Raman spectrum-based tissue component measurement method and device, and wearable device

Abstract

Embodiments of the present disclosure provide a Raman spectrum-based tissue component measurement method, device and wearable equipment. The method comprises: irradiating a measurement region with incident light of a first preset wavelength, the incident light of the first preset wavelength forming at least one beam of Raman scattered light of a second preset wavelength after passing through the measurement region and exiting from an exit position, wherein a wavelength difference between the first preset wavelength and the second preset wavelength is determined according to a preset Raman shift; acquiring Raman intensity corresponding to each beam of Raman scattered light collected by a measurement probe, wherein a tissue component measurement device provided with the measurement probe has a signal-to-noise ratio level meeting a resolution of an expected change in concentration of a tissue component; and determining a concentration of a measured tissue component according to at least one Raman intensity corresponding to the second preset wavelength.

Description

TECHNICAL FIELD

[0001] The present disclosure relates to the technical field of spectrum measurement, and more particularly, to a Raman spectrum based tissue composition measurement method and device and wearable equipment. BACKGROUND

[0002] Since the energy change of photons in Raman scattering usually originates from the superposition of molecular vibration energy and incident photon energy, the Raman scattering light includes rich information of molecular vibration structure. Since the spectral features of Raman spectra of different molecules are different, they can be used as fingerprint spectra for molecular identification. Raman spectrum can be used to determine the composition of different substances according to the difference in intermolecular vibration frequency, which makes it possible to measure the composition of tissue based on Raman spectrum. Moreover, Raman spectrum has the advantages of clear and sharp characteristic peaks, which are not easy to overlap, and weak Raman intensity of water, etc. Therefore, Raman spectrum technology is considered to be one of the most promising technologies for tissue composition measurement. The tissue composition can include blood glucose, hemoglobin, fat, protein, etc.

[0003] In the process of implementing the present disclosure, the inventors have found that at least the following problem exists in the related art: it is difficult to obtain a real tissue composition signal in the related art. SUMMARY

[0004] Therefore, the present disclosure provides a Raman spectrum based tissue composition measurement method, device and wearable equipment.

[0005] One aspect of the present disclosure provides a Raman spectrum based tissue composition measurement method, which comprises: irradiating a measurement region with incident light of a first preset wavelength, the incident light of the first preset wavelength being emitted from an exit position after passing through the measurement region to form at least one beam of Raman scattering light of a second preset wavelength, wherein the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to a preset Raman shift; acquiring Raman intensity corresponding to each beam of Raman scattering light collected by a measurement probe, wherein a tissue composition measurement device provided with the measurement probe has a signal-to-noise ratio level that meets the resolution of the expected tissue composition concentration change; and determining the concentration of the measured tissue composition according to at least one Raman intensity corresponding to the second preset wavelength.

[0006] Another aspect of the embodiments of the present disclosure provides a tissue component measurement device based on Raman spectrum, comprising: a light source module configured to irradiate a measurement region with incident light of a first preset wavelength, the incident light of the first preset wavelength forms at least one beam of Raman scattered light of a second preset wavelength after passing through the measurement region and being emitted from an exit position, wherein a wavelength difference between the first preset wavelength and the second preset wavelength is determined according to a preset Raman shift; a collection module configured to acquire Raman intensity corresponding to each of the Raman scattered light collected by a measurement probe, wherein the tissue component measurement device provided with the measurement probe has a signal-to-noise ratio level that meets a requirement of distinguishing a change in concentration of an intended tissue component; and a processing module configured to determine a concentration of a measured tissue component according to at least one Raman intensity corresponding to the second preset wavelength.

[0007] Another aspect of the embodiments of the present disclosure provides a wearable device comprising the tissue component measurement device based on Raman spectrum as described above.

[0008] According to the embodiments of the present disclosure, by irradiating a measurement region with incident light of a first preset wavelength, the incident light of the first preset wavelength forms at least one beam of Raman scattered light of a second preset wavelength after passing through the measurement region and being emitted from an exit position, a wavelength difference between the first preset wavelength and the second preset wavelength is determined according to a preset Raman shift, Raman intensity corresponding to each of the Raman scattered light collected by a measurement probe is acquired, the tissue component measurement device provided with the measurement probe has a signal-to-noise ratio level that meets a requirement of distinguishing a change in concentration of an intended tissue component, and a concentration of a measured tissue component is determined according to at least one Raman intensity corresponding to the second preset wavelength. Since the tissue component measurement device provided with the measurement probe has the signal-to-noise ratio level that meets the requirement of distinguishing the change in concentration of the intended tissue component, the ability of perceiving the change in concentration of the intended tissue component is achieved, and thus the possibility of acquiring a real signal of the measured tissue component is improved. BRIEF DESCRIPTION OF DRAWINGS

[0009] The above and other objects, features and advantages of the present disclosure will become more apparent from the following description when taken in conjunction with the accompanying drawings, in which:

[0010] Figure 1 A flowchart of a tissue component measurement method based on Raman scattering according to an embodiment of the present disclosure is schematically shown;

[0011] Figure 2 A schematic diagram of receiving Raman scattered light by a smaller area of a light receiving surface when shaking occurs according to an embodiment of the present disclosure is schematically shown;

[0012] Figure 3A schematic diagram of receiving Raman scattered light by a larger area of a photosensitive surface when jitter occurs is shown according to an embodiment of the present disclosure;

[0013] Figure 4 A schematic diagram of measurement results obtained based on a Monte Carlo simulation method is shown according to an embodiment of the present disclosure;

[0014] Figure 5 A schematic diagram of differential measurement is shown according to an embodiment of the present disclosure;

[0015] Figure 6 A schematic diagram of positioning a measurement region based on an optical method is shown according to an embodiment of the present disclosure;

[0016] Figure 7 A schematic diagram of positioning a measurement region based on another optical method is shown according to an embodiment of the present disclosure;

[0017] Figure 8 A schematic diagram of positioning a measurement region based on an image matching method is shown according to an embodiment of the present disclosure;

[0018] Figure 9 A schematic diagram of positioning a measurement region based on another image matching method is shown according to an embodiment of the present disclosure;

[0019] Figure 10 A schematic diagram of positioning a measurement region based on an imaging method is shown according to an embodiment of the present disclosure;

[0020] Figure 11 A schematic diagram of positioning a measurement region based on another imaging method is shown according to an embodiment of the present disclosure;

[0021] Figure 12 A schematic diagram of positioning a measurement posture based on an optical method is shown according to an embodiment of the present disclosure;

[0022] Figure 13 A schematic diagram of positioning a measurement posture based on an image matching method is shown according to an embodiment of the present disclosure;

[0023] Figure 14 A schematic diagram of positioning a measurement posture based on an imaging method is shown according to an embodiment of the present disclosure;

[0024] Figure 15 A schematic diagram of obtaining a photosensitive surface by setting a mask plate on an initial photosensitive surface is shown according to an embodiment of the present disclosure;

[0025] Figure 16A block diagram of a Raman scattering based tissue composition measurement device according to an embodiment of the present disclosure is schematically shown;

[0026] Figure 17 A schematic diagram of diffuse measurement according to an embodiment of the present disclosure is schematically shown;

[0027] Figure 18 A schematic diagram of a stereoscopic photosurface in the form of a glove according to an embodiment of the present disclosure is schematically shown;

[0028] Figure 19 A schematic diagram of another stereoscopic photosurface in the form of a glove according to an embodiment of the present disclosure is schematically shown;

[0029] Figure 20 A schematic diagram of a stereoscopic photosurface in the form of a bracelet according to an embodiment of the present disclosure is schematically shown;

[0030] Figure 21 A schematic diagram of another stereoscopic photosurface in the form of a bracelet according to an embodiment of the present disclosure is schematically shown;

[0031] Figure 22 A schematic diagram of a stereoscopic photosurface for arm measurement according to an embodiment of the present disclosure is schematically shown;

[0032] Figure 23 A schematic diagram of an anode electrical connection of different photosurfaces according to an embodiment of the present disclosure is schematically shown;

[0033] Figure 24 A schematic diagram of a positional relationship between a fixing portion and a measurement probe according to an embodiment of the present disclosure is schematically shown;

[0034] Figure 25 A structural schematic diagram of a fixing portion according to an embodiment of the present disclosure is schematically shown;

[0035] Figure 26 A schematic diagram of a first fitting member according to an embodiment of the present disclosure is schematically shown;

[0036] Figure 27 A schematic diagram of another first fitting member according to an embodiment of the present disclosure is schematically shown;

[0037] Figure 28 A schematic diagram of a region positioning portion according to an embodiment of the present disclosure is schematically shown;

[0038] Figure 29 A schematic diagram of another region positioning portion according to an embodiment of the present disclosure is schematically shown;

[0039] Figure 30A schematic diagram of a first image acquisition unit is shown schematically according to an embodiment of the present disclosure;

[0040] Figure 31 A schematic diagram of a first posture positioning unit is shown schematically according to an embodiment of the present disclosure;

[0041] Figure 32 A schematic diagram of a third image acquisition unit is shown schematically according to an embodiment of the present disclosure;

[0042] Figure 33 A schematic diagram of a measurement posture and measurement region positioning is shown schematically according to an embodiment of the present disclosure;

[0043] Figure 34 A schematic diagram of another measurement posture and measurement region positioning is shown schematically according to an embodiment of the present disclosure;

[0044] Figure 35 A schematic diagram of a first sleeve provided on a measurement probe is shown schematically according to an embodiment of the present disclosure;

[0045] Figure 36 A schematic diagram of a second sleeve provided externally on a target region of a first sleeve is shown schematically according to an embodiment of the present disclosure;

[0046] Figure 37 A schematic diagram of a photosensitive surface receiving outgoing light without filling a refractive index matching material is shown schematically according to an embodiment of the present disclosure;

[0047] Figure 38 A schematic diagram of a photosensitive surface receiving outgoing light with filling a refractive index matching material is shown schematically according to an embodiment of the present disclosure;

[0048] Figure 39 A schematic diagram of another photosensitive surface receiving outgoing light with filling a refractive index matching material is shown schematically according to an embodiment of the present disclosure;

[0049] Figure 40 A schematic diagram of a wearable device is shown schematically according to an embodiment of the present disclosure;

[0050] Figure 41 A schematic diagram of an assembly process of a wearable device is shown schematically according to an embodiment of the present disclosure;

[0051] Figure 42 A schematic diagram of a wearable device is shown schematically according to an embodiment of the present disclosure;

[0052] Figure 43 A diagram illustrating a case where a wearable device measures an average optical path of outgoing light received by a probe so that a moving amplitude of skin at a measurement region is less than or equal to a moving amplitude threshold value, and the average optical path of the outgoing light received by the probe is maintained within a preset optical path range during skin jitter, according to an embodiment of the disclosure is schematically illustrated. DETAILED DESCRIPTION

[0053] Hereinafter, embodiments of the disclosure will be described with reference to the accompanying drawings. It should be understood, however, that the description which follows is merely illustrative and is not intended to limit the scope of the disclosure. In the following detailed description of embodiments of the disclosure, numerous specific details are set forth in order to provide a thorough understanding of the embodiments of the disclosure. However, it will be apparent to one skilled in the art that the embodiments of the disclosure can be practiced without these specific details. In other instances, well-known structures and functions have not been described in detail in order to avoid obscuring the concepts of the disclosure.

[0054] The terms used herein are merely used to describe specific embodiments and are not intended to limit the disclosure. The terms "include", "comprise" and the like used herein indicate the presence of the described features, steps, operations, and / or components, but do not exclude the presence or addition of one or more other features, steps, operations, or components.

[0055] All terms used herein, including technical and scientific terms, have the same meanings as those generally understood by those skilled in the art unless otherwise defined. It should be noted that the terms used herein should be interpreted as having meanings consistent with the context of the specification, and should not be interpreted in an idealized or overly formal manner.

[0056] In the case of using expressions similar to "among A, B, and C, etc.", in general, it should be interpreted according to the meaning that a person skilled in the art generally understands the expression (for example, "a system having A, B, and C" should include but is not limited to a system having A alone, a system having B alone, a system having C alone, a system having A and B, a system having A and C, a system having B and C, and / or a system having A, B, C, etc.). In the case of using expressions similar to "among A, B, or C, etc.", in general, it should be interpreted according to the meaning that a person skilled in the art generally understands the expression (for example, "a system having A, B, or C" should include but is not limited to a system having A alone, a system having B alone, a system having C alone, a system having A and B, a system having A and C, a system having B and C, and / or a system having A, B, C, etc.).

[0057] When the incident light irradiates the measured object, the measured object causes two types of scattering of the incident light, i.e., Rayleigh scattering and Raman scattering. Among them, the Rayleigh scattering only changes the transmission direction of the incident light, and does not change the frequency of the incident light. The Raman scattering not only changes the transmission direction of the incident light, but also changes the frequency of the Raman scattering light. The difference between the frequency of the Raman scattering light and the frequency of the incident light is called Raman shift. The Raman shift is independent of the frequency of the incident light, and is only related to the molecular structure of the measured tissue component itself, depends on the change of the molecular vibration energy level, different chemical bonds or groups in the molecule have different characteristic molecular vibrations, which is the basis for Raman spectrum to analyze different tissue components.

[0058] Because the absorption of the measured tissue component itself is usually weak, and the concentration range of the measured tissue component of the measured object itself is usually not large, the measured tissue component signal is usually weak. And the change of the measurement condition will easily drown out the weak measured tissue component signal. In addition, the intensity of the Raman scattering light of the measured tissue component that can be collected is also very weak, which can be called Raman intensity. The measured tissue component signal represents the change of the Raman intensity caused by the concentration change of the measured tissue component.

[0059] In the process of realizing the present disclosure, the inventors found that the main reason why the related art does not realize reliable Raman scattering-based tissue component measurement is that.

[0060] Firstly, the importance of directly obtaining the real measured tissue component signal is not recognized, and it is not recognized that it is a prerequisite for realizing the non-invasive measurement of the living tissue component.

[0061] Secondly, an effective solution to directly obtain the real measured tissue component signal is not found. Because it is a very difficult problem to directly obtain the real measured tissue component signal, even if it is realized that there is the above problem, there is no effective solution to solve the above problem.

[0062] Thirdly, too much reliance is placed on the reliability of the multivariate analysis method. Because the tissue components (such as hemoglobin, water and glucose, etc.) and the physical state (such as temperature and pressure, etc.) have characteristic absorption in the preset waveband, it is generally believed that the multivariate analysis method is a potential tool for interference correction in the measurement of the living tissue component, such as using the multivariate analysis method to process the multi-wavelength spectral data, i.e., establishing a mathematical model between the optical signal and the true value of the concentration of the measured tissue component by the multivariate analysis method, and using the established mathematical model to predict the concentration of the measured tissue component, so as to indirectly obtain the measured tissue component signal. Among them, the preset waveband can include visible-near infrared waveband.

[0063] Some researchers overestimate the reliability of multivariate analysis methods due to the above-mentioned performance of multivariate analysis methods. However, the signal change caused by the change of the measurement condition is usually much larger than the signal change caused by the change of the concentration of the measured tissue component. Therefore, the measurement result obtained by using the multivariate analysis method is likely to have a casual correlation with the signal change caused by the interference (for example, physiological background interference) other than the measured tissue component, and the result obtained by using the indirect extraction method of the signal of the measured tissue component is likely to be a pseudo-correlation result.

[0064] To solve the above-mentioned problem, the inventors believe that the first condition for obtaining the real signal of the measured tissue component is that the measurement device for measuring the tissue component has the ability to perceive the expected change of the concentration of the tissue component. The expected change of the concentration of the tissue component can be understood as the limit measurement accuracy. The limit measurement accuracy can be understood as that when the change of the light energy caused by the change of the concentration of the measured tissue component (i.e., the measurement value) is equivalent to the noise level of the instrument, the measurement value is difficult to be extracted from the noise. This minimum perceivable change of the concentration of the measured tissue component is called the limit measurement accuracy, and the device for measuring the tissue component is called the tissue component measurement device.

[0065] To realize that the tissue component measurement device has the ability to perceive the expected change of the concentration of the tissue component, the inventors propose a scheme for measuring the tissue component by using a tissue component measurement device having a signal-to-noise ratio level for resolving the expected change of the concentration of the tissue component. The tissue component measurement device having the signal-to-noise ratio level for resolving the expected change of the concentration of the tissue component can be realized by improving the efficiency of the Raman scattered light. The specific embodiments will be described below.

[0066] Figure 1 A flowchart of a Raman scattering-based tissue component measurement method according to an embodiment of the present disclosure is schematically shown.

[0067] As shown in Figure 1 , the method includes operations S110-S130.

[0068] In operation S110, a measurement region is irradiated with incident light of a first preset wavelength, and the incident light of the first preset wavelength is emitted from an exit position to form at least one beam of Raman scattered light of a second preset wavelength after passing through the measurement region, wherein the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to a preset Raman shift.

[0069] According to an embodiment of the present disclosure, different measurement sites have different skin characteristics, which can include smoothness, presence or absence of hair, flatness, skin thickness, and softness. Therefore, a suitable measurement site needs to be selected according to actual conditions, such as the structure of the measurement probe. The measurement site can include at least one of a finger, a palm, an arm, a forehead, and an earlobe. The measurement region can be a region on the measurement site.

[0070] When the measurement region is irradiated with incident light of the first preset wavelength, Raman scattered light of the second preset wavelength is generated, and the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to a preset Raman shift. The preset Raman shift is determined according to the specificity of the first preset wavelength of the incident light for the measured tissue component.

[0071] According to an embodiment of the present disclosure, the second preset wavelength can be a wavelength sensitive to the measured tissue component. The wavelength band to which the second preset wavelength belongs can include an ultraviolet wavelength band, a visible light wavelength band, a near-infrared wavelength band, a mid-infrared wavelength band, or a far-infrared wavelength band.

[0072] In operation S120, the Raman intensity corresponding to each Raman scattered light collected by the measurement probe is obtained. The tissue component measurement device provided with the measurement probe has a signal-to-noise ratio level that can distinguish the expected change in the concentration of the tissue component.

[0073] According to an embodiment of the present disclosure, the expected change in the concentration of the tissue component can be set according to actual conditions. The tissue component measurement device provided with the measurement probe has a signal-to-noise ratio level that can distinguish the expected change in the concentration of the tissue component. This can be achieved by the following method. The total area of the same type of photosensitive surface provided on the measurement probe is large, and the area of each photosensitive surface in the same type of photosensitive surface is continuous, so that the efficiency of receiving Raman scattered light is improved.

[0074] In operation S130, the concentration of the measured tissue component is determined according to at least one Raman intensity corresponding to the second preset wavelength.

[0075] According to an embodiment of the present disclosure, the at least one Raman intensity corresponding to the second preset wavelength can be processed based on an interference suppression method to determine the concentration of the measured tissue component. The interference suppression method can include a differential measurement method, which can include a time differential measurement method or a position differential measurement method. Alternatively, the at least one Raman intensity can also be processed based on a non-differential measurement method to determine the concentration of the measured tissue component.

[0076] According to the technical scheme of the embodiment of the present disclosure, the measurement region is irradiated by the incident light of the first preset wavelength, the incident light of the first preset wavelength is emitted from the exit position to form at least one Raman scattering light of the second preset wavelength after passing through the measurement region, the wavelength difference between the first preset wavelength and the second preset wavelength is determined according to the preset Raman shift, the Raman intensity corresponding to each Raman scattering light collected by the measurement probe is obtained, the tissue component measurement device provided with the measurement probe has a signal-to-noise ratio level that can distinguish the expected change of the concentration of the tissue component, and the concentration of the measured tissue component is determined according to at least one Raman intensity corresponding to the second preset wavelength. Since the tissue component measurement device provided with the measurement probe has a signal-to-noise ratio level that can distinguish the expected change of the concentration of the tissue component, the ability to perceive the expected change of the concentration of the tissue component is achieved, and the possibility of obtaining a real signal of the measured tissue component is improved.

[0077] According to the embodiment of the present disclosure, the Raman intensity corresponding to each Raman scattering light collected by the measurement probe can include the following operations.

[0078] In the case of shielding the fluorescence interference, the Raman intensity corresponding to each Raman scattering light collected by the measurement probe is obtained.

[0079] According to the embodiment of the present disclosure, if the measured object has a fluorescence effect, the incident light will produce fluorescence at the same time of producing Raman scattering light, and the fluorescence will have an adverse effect on the measurement result.

[0080] In order to reduce the adverse effect of fluorescence on the measurement result, a method of shielding fluorescence interference can be used to shield the fluorescence, and in the case of shielding the fluorescence interference, the Raman intensity corresponding to the Raman scattering light collected by the measurement probe is obtained. The method of shielding fluorescence interference can include a baseline correction method based on a mathematical algorithm, a method of selecting a suitable preset wavelength, a surface-enhanced Raman spectroscopy method, a double-wavelength excitation frequency shift method, and a time-gated method.

[0081] According to the embodiment of the present disclosure, the method can further include the following operations.

[0082] The fluorescence interference is shielded based on the time-gated method.

[0083] According to the embodiment of the present disclosure, since the time of producing fluorescence is later than that of producing Raman scattering light, the Raman scattering light can be collected by using a gating signal, and the fluorescence can be shielded.

[0084] According to the embodiment of the present disclosure, the same incident light is irradiated to different incident positions by a light splitting method.

[0085] According to the embodiment of the present disclosure, in order to reduce the incident light intensity of the incident light per unit area, a multi-point incident method can be used, that is, the same incident light is incident from at least two incident positions.

[0086] According to an embodiment of the present disclosure, the measurement probe includes M photosensitive surfaces. The Raman intensity corresponding to each Raman scattering light collected by the measurement probe is acquired, and the tissue component measurement device provided with the measurement probe has a signal-to-noise ratio level that meets the resolution of the expected change in the concentration of the tissue component, which can include the following operations.

[0087] The light intensity values corresponding to each Raman scattering light collected by the M photosensitive surfaces are acquired to obtain T Raman intensities, wherein each Raman intensity is processed from the light intensity values of the Raman scattering light collected by one or more photosensitive surfaces, the total area of the same type of photosensitive surface is greater than or equal to the area threshold, and the area of each photosensitive surface in the same type of photosensitive surface is continuous, the same type of photosensitive surface includes one or more photosensitive surfaces, the same type of photosensitive surface is used to output one Raman intensity, 1≤T≤M, so that the tissue component measurement device has a signal-to-noise ratio level that meets the resolution of the expected change in the concentration of the tissue component.

[0088] According to an embodiment of the present disclosure, each photosensitive surface in the M photosensitive surfaces can be used individually, partially combined or fully combined, and the combined use means outputting one Raman intensity. In an embodiment of the present disclosure, the photosensitive surface used to output one Raman intensity is referred to as the same type of photosensitive surface, and the same type of photosensitive surface can include one or more photosensitive surfaces. The condition for combining different photosensitive surfaces can be that the average optical path of the Raman scattering light received by each photosensitive surface is within an average optical path range. The average optical path range can be a range composed of greater than or equal to a first average optical path threshold and less than or equal to a second average optical path threshold. The first average optical path threshold and the second average optical path threshold can be determined according to an average optical path and an optical path variation amplitude. The average optical path is an average value calculated according to the average optical path of the Raman scattering light received by each photosensitive position of the same type of photosensitive surface. For example, if the average optical path is a and the optical path variation amplitude is ±30%, the first average optical path threshold can be 0.7a and the second average optical path threshold can be 1.3a.

[0089] The average optical path is described as follows. The transmission path of light in tissue can be represented by an optical path and a penetration depth, wherein the optical path is used to represent the total distance of light transmission in tissue, and the penetration depth is used to represent the maximum longitudinal distance that light can reach in tissue. For a determined source-probe distance, the average optical path is used to represent the average value of the optical path of light in tissue. The probability distribution function of the optical path can be understood as a function of the source-probe distance and the optical parameters of the tissue, wherein the source-probe distance represents the radial distance between the center of the incident light and the center of the photosensitive surface. Correspondingly, in mathematical expression, the average optical path can be understood as a function of the source-probe distance and the optical parameters of the tissue, wherein the optical parameters of the tissue can include the absorption coefficient, the scattering coefficient and the anisotropy factor. The factors affecting the average optical path can include the absorption coefficient, the scattering coefficient, the anisotropy factor and the source-probe distance.

[0090] According to an embodiment of the present disclosure, each photosensitive surface can be a ring-shaped photosensitive surface or a non-ring-shaped photosensitive surface. The non-ring-shaped photosensitive surface can include a sector ring photosensitive surface, a circular photosensitive surface, a sector photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface. The polygonal photosensitive surface can include a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

[0091] The same type of photosensitive surface can be a ring-shaped photosensitive surface or a non-ring-shaped photosensitive surface. When the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent ring-shaped photosensitive surface. When the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a ring-shaped photosensitive surface formed by combining the multiple photosensitive surfaces. When the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-ring-shaped photosensitive surface. When the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a non-ring-shaped photosensitive surface formed by combining the multiple photosensitive surfaces.

[0092] In order to make the tissue composition measuring device provided with the measuring probe have a signal-to-noise ratio level that meets the expected change in tissue composition concentration, a method for improving the efficiency of the measuring probe in receiving Raman scattered light can be used.

[0093] In order to improve the efficiency of the measuring probe in receiving Raman scattered light, a large-area photosensitive surface (i.e., a large-area photosensitive surface) can be used, that is, the total photosensitive surface area of the same type of photosensitive surface is greater than or equal to an area threshold, and the area of each photosensitive surface in the same type of photosensitive surface is continuous. The photosensitive surface is made of photosensitive material, which is different from single-point fiber reception and multiple single-fiber joint reception. Since the large-area photosensitive surface can achieve a large range of Raman scattered light reception, the efficiency of receiving Raman scattered light can be improved. In addition, by arranging the photosensitive surface close to the surface of the measurement area, a higher Raman scattered light efficiency can be achieved.

[0094] According to an embodiment of the present disclosure, the material of the photosensitive surface can be determined according to the second preset wavelength. For example, if the second preset wavelength belongs to the near-infrared waveband, the material of the photosensitive surface can be indium gallium arsenide.

[0095] According to an embodiment of the present disclosure, each photosensitive surface can collect the light intensity value of the Raman scattered light emitted from the exit position within the preset anti-shake range corresponding to the photosensitive surface.

[0096] According to embodiments of the present disclosure, in the process of implementing the present disclosure concept, the inventors have also found that if only the intensity distribution of the light spot of the incident light irradiating to the measurement region is changed while other conditions remain unchanged, the obtained measurement results are different. If the photosensitive surface is arranged close to the blood vessel, the obtained measurement result is better than that obtained by arranging the same photosensitive surface away from the blood vessel while other conditions remain unchanged. The measurement result can be represented by the relative variation amount of the light intensity value of the Raman scattered light received by the photosensitive surface or the standard deviation of the light intensity value. In the study of the reasons for the different measurement results, it is found that changing the intensity distribution of the light spot of the incident light irradiating to the measurement region can reflect the randomness of the light source irradiation, and the distance from the blood vessel can reflect the strength of the pulse beat, and both the randomness of the light source irradiation and the pulse beat are the sources of the jitter. Therefore, it is found that one of the reasons for the difficulty in obtaining reliable measurement results is the jitter.

[0097] On the basis of the study of the jitter, it is found that according to the sources of the jitter, it can be divided into internal sources and external sources. In addition to the pulse beat, the internal sources can also include physiological background changes. In addition to the randomness of the light source irradiation, the external sources can also include the uncertainty of the transmission of the incident light itself. The randomness of the light source irradiation can be reflected by the intensity distribution of the light spot of the incident light irradiating to the measurement region. It is found that whether the jitter is caused by the internal sources or the external sources, it will affect the transmission path of the light in the tissue, and further affect the intensity distribution of the Raman scattered light on the measurement region. In order to solve the problem of difficulty in obtaining the true measured tissue component signal caused by the jitter, the inventors have found that a photosensitive surface with a large area (i.e. a large-area photosensitive surface) can be used to collect the light intensity value of the Raman scattered light, so as to effectively suppress the adverse effects of the jitter on the measurement results. That is, the large-area photosensitive surface can effectively suppress the adverse effects of the jitter, and the so-called "large-area photosensitive surface" can be understood as the area of the photosensitive surface is large enough to collect the light intensity value of the Raman scattered light emitted from the exit position within a preset jitter range. The reasons why the scheme of using a large-area photosensitive surface to collect the Raman intensity of the Raman scattered light can effectively suppress the adverse effects of the jitter on the measurement results will be described below.

[0098] Since the large-area photosensitive surface can increase the proportion of the area in the photosensitive surface that can stably receive the Raman scattered light, the stability of receiving the Raman scattered light can be improved, and the adverse effects of the change of the intensity distribution of the Raman scattered light caused by the jitter can be reduced, thereby improving the possibility of obtaining the true measured tissue component signal. The stability can be represented by the relative variation amount of the light intensity value of the Raman scattered light received by the photosensitive surface or the standard deviation of the light intensity value. The smaller the relative variation amount of the light intensity value, the higher the stability, and the smaller the standard deviation of the light intensity value, the higher the stability.

[0099] For example, the jitter caused by the pulse is described. The pulse can be reflected by the blood vessel state. Figure 2 A schematic diagram of receiving Raman scattering light by a smaller area of the light receiving surface when jitter occurs is shown. Figure 3 A schematic diagram of receiving Raman scattering light by a larger area of the light receiving surface when jitter occurs is shown. Figure 2 and Figure 3 The jitter occurs. Figure 2 and Figure 3 Both are square light receiving surfaces. Figure 2 The area of the light receiving surface A in the first case is smaller than Figure 3 The area of the light receiving surface B. Figure 4 and Figure 5 In the first case, the blood vessel state 1 represents a blood vessel contraction state, and the blood vessel state 2 represents a blood vessel dilation state. In the second case, the skin state 1 represents a skin state corresponding to the blood vessel state 1, and the skin state 2 represents a skin state corresponding to the blood vessel state 2. The skin state 1 to the skin state 2 reflect the jitter.

[0100] In the case of the same jitter, the measurement results obtained by using light receiving surfaces with different areas are compared. The measurement result is represented by the relative change amount of the light intensity value of the Raman scattering light received by the light receiving surface within a preset time period or the standard deviation of the light intensity value. The relative change amount of the light intensity value can be determined by calculating the difference between the maximum light intensity value and the minimum light intensity value within the preset time period, calculating the average value of the exit value within the preset time period, and calculating the ratio of the difference to the average value. The ratio is taken as the relative change amount of the light intensity value. The preset time period can be one pulse period.

[0101] The measurement results also show that whether the relative change amount of the light intensity value of the Raman scattering light received by the light receiving surface is used to represent the measurement result, or the standard deviation of the light intensity value of the Raman scattering light received by the light receiving surface is used to represent the measurement result, the measurement result obtained by using the light receiving surface B is better than the measurement result obtained by using the light receiving surface A.

[0102] Since the area of the light receiving surface B is larger than the area of the light receiving surface A, it can be explained that the large-area light receiving surface can improve the stability of receiving the Raman scattering light, and thus can reduce the adverse effects of the change of the intensity distribution of the Raman scattering light caused by the jitter, thereby improving the possibility of obtaining the real measured tissue component signal.

[0103] It should be noted that the large-area photosensitive surface described in the embodiments of the present disclosure can achieve higher stability and efficiency of Raman scattered light in the case that the distance from the surface of the measurement area is small, that is, in the case that the surface of the measurement area is close. This cannot be achieved by using single-point fiber receiving and multiple single-fiber joint receiving, because firstly, it is limited by the numerical aperture of the fiber; secondly, it is limited by the state change of the fiber. The state of the fiber is easily affected by the environment, and its change has a great influence on the stability of receiving Raman scattered light.

[0104] It should also be noted that in order to improve the signal-to-noise ratio of Raman intensity, a large-area photosensitive surface can be used. In other words, the large-area photosensitive surface not only plays a role in improving the efficiency of Raman intensity, but also plays a role in effectively suppressing jitter.

[0105] In order to improve the reliability of the measurement result, it is necessary to ensure that each photosensitive surface can collect the light intensity value of the Raman scattered light emitted from the exit position within the preset anti-jitter range corresponding to the photosensitive surface as much as possible, which requires the area of the photosensitive surface to be as large as possible. Each photosensitive surface has a corresponding preset anti-jitter range, and the preset anti-jitter ranges of different photosensitive surfaces are the same or different. In the following, the effect of suppressing jitter is better as the area of the photosensitive surface is larger will be explained from three aspects with examples. It is assumed that the area of the photosensitive surface A is smaller than the area of the photosensitive surface B. The photosensitive surface A and the photosensitive surface B are both square photosensitive surfaces.

[0106] Firstly, the jitter caused by pulse beats is suppressed. The photosensitive surface A and the photosensitive surface B are arranged at the same position on the measurement area, which is close to the blood vessel. Under the same other conditions, the measurement results obtained by using the photosensitive surface A and the photosensitive surface B are compared, wherein the measurement result is represented by the relative change amount of the light intensity value of the Raman scattered light received by the photosensitive surface within a pulse period or the standard deviation of the light intensity value. The calculation method of the relative change amount of the light intensity value is as described above, and will not be repeated here. It is found that the relative change amount of the light intensity value of the Raman scattered light received by the photosensitive surface B is smaller than the relative change amount of the light intensity value of the Raman scattered light received by the photosensitive surface A, and the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface B is smaller than the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface A. Therefore, it can be concluded that whether the relative change amount of the light intensity value of the Raman scattered light received by the photosensitive surface represents the measurement result or the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface represents the measurement result, the measurement result obtained by using the photosensitive surface B is better than the measurement result obtained by using the photosensitive surface A.

[0107] Since the measurement result obtained by using the photosensitive surface B is better than the measurement result obtained by using the photosensitive surface A, and the area of the photosensitive surface B is larger than the area of the photosensitive surface A, it can be concluded that the larger the area of the photosensitive surface is, the better the effect of suppressing the jitter caused by pulse beats is.

[0108] Secondly, the jitter caused by the change of the intensity distribution of the light spot irradiated by the incident light to the measurement region is inhibited. In the case where other conditions are unchanged, only the intensity distribution of the light spot irradiated by the incident light to the measurement region is changed. The measurement results obtained by using the photosensitive surface A and the photosensitive surface B are compared, wherein the measurement result is characterized by the relative change amount of the light intensity value or the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface within a preset time period. The calculation method of the relative change amount of the light intensity value is as described above, and will not be described here again. It is found that the change amount of the light intensity value of the Raman scattered light received by the photosensitive surface B is smaller than the change amount of the light intensity value of the Raman scattered light received by the photosensitive surface A, and the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface B is smaller than the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface A. Therefore, it can be concluded that no matter whether the relative change amount of the light intensity value of the Raman scattered light received by the photosensitive surface is used to characterize the measurement result or the standard deviation of the light intensity value of the Raman scattered light received by the photosensitive surface is used to characterize the measurement result, the measurement result obtained by using the photosensitive surface B is better than the measurement result obtained by using the photosensitive surface A.

[0109] Since the measurement result obtained by using the photosensitive surface B is better than the measurement result obtained by using the photosensitive surface A, and the area of the photosensitive surface B is larger than the area of the photosensitive surface A, it can be concluded that the larger the area of the photosensitive surface is, the better the effect of inhibiting the jitter caused by the change of the intensity distribution of the light spot irradiated by the incident light to the measurement region is.

[0110] Thirdly, the jitter caused by the uncertainty of the transmission of the incident light itself is inhibited. The Monte Carlo simulation method is used. The number of photons is 10 15 The center of the incident light is incident, the photosensitive surface A and the photosensitive surface B are respectively arranged at a distance of 2.4 mm from the center of the incident light, and the simulation number is 22. The measurement results obtained by using the photosensitive surface A and the photosensitive surface B are compared, wherein the measurement result is characterized by the standard deviation of the number of Raman scattered photons per unit area, and the smaller the standard deviation of the number of Raman scattered photons per unit area is, the better the inhibition effect is. Figure 5 A schematic diagram of a measurement result obtained based on the Monte Carlo simulation method according to an embodiment of the present disclosure is schematically shown. It is found that the standard deviation of the number of Raman scattered photons per unit area corresponding to the photosensitive surface B is smaller than the standard deviation of the number of Raman scattered photons per unit area corresponding to the photosensitive surface A. That is, the measurement result obtained by using the photosensitive surface B is better than the measurement result obtained by using the photosensitive surface A.

[0111] Since the measurement result obtained by using the photosensitive surface B is better than the measurement result obtained by using the photosensitive surface A, and the area of the photosensitive surface B is larger than the area of the photosensitive surface A, it can be concluded that the larger the area of the photosensitive surface is, the better the effect of inhibiting the jitter caused by the uncertainty of the transmission of the incident light itself is.

[0112] Through the above three examples, it is illustrated that the larger the area of the light-receiving surface is, the better the effect of suppressing the adverse effects of the jitter on the measurement results is.

[0113] According to an embodiment of the present disclosure, the proportion of the average optical path of the Raman scattered light received by each light-receiving surface in the target tissue layer in the total optical path is greater than or equal to a proportion threshold, wherein the total optical path is the total distance of the Raman scattered light transmitted in the measurement region.

[0114] According to an embodiment of the present disclosure, the tissue model of the measured object is generally a layered structure, that is, it can be divided into one or more layers. Different tissue layers carry different information of the measured tissue component, and in order to improve the possibility of obtaining the real signal of the measured tissue component, it is necessary to make the transmission path of the Raman scattered light mainly pass through the tissue layer carrying more information of the measured tissue component. The target tissue layer can be understood as a tissue layer carrying more information of the measured tissue component, or a tissue layer being the main source of the measured tissue component. The following takes the human body as the measured object and the blood glucose as the measured tissue component for example.

[0115] The skin tissue model of the human body can be understood as a three-layer model, which includes the epidermis layer, the dermis layer and the subcutaneous fat layer from outside to inside. Among them, the epidermis layer contains a small amount of interstitial fluid and does not contain plasma and lymph fluid. The dermis layer contains a large amount of interstitial fluid, and also contains more plasma and a small amount of lymph fluid due to the presence of rich capillary blood vessels. The subcutaneous fat layer contains a small amount of cell fluid, and contains a large amount of plasma and a small amount of lymph fluid due to the presence of blood vessels such as veins and arteries. As can be seen, different tissue layers carry different information of the measured tissue component.

[0116] Since the epidermis layer contains a small amount of interstitial fluid, the epidermis layer is not a suitable source of blood glucose information. Although the subcutaneous fat layer contains a large amount of plasma and a relatively small amount of interstitial fluid, it is not a suitable source of blood glucose information due to the limitation of the penetration depth of the incident light. Since the dermis layer contains rich capillary blood vessels and a large amount of interstitial fluid, and the incident light can easily reach the dermis layer, the dermis layer can be used as the main source of blood glucose information. Accordingly, the target tissue layer can be the dermis layer.

[0117] According to an embodiment of the present disclosure, the average optical path of the Raman scattered light in each tissue layer can be determined according to the optical path and the penetration depth.

[0118] In order to ensure that the transmission path of the Raman scattered light is mainly through the Raman scattered light of the target tissue layer, it is necessary to make the proportion of the average optical path of the Raman scattered light received by each photosensitive surface in the target tissue layer in the total optical path greater than or equal to a proportion threshold, wherein the total optical path can be the total distance of the Raman scattered light in the measurement region, that is, the total distance of the incident light from entering the measurement region, transmitting in the measurement region, and reaching the exit position. Wherein the proportion threshold is related to the source-probe distance between the center of the photosensitive surface and the center of the incident light and the tissue optical parameter.

[0119] It should be noted that, since the embodiment of the present disclosure limits the proportion of the average optical path of the Raman scattered light received by the photosensitive surface in the target tissue layer in the total optical path, the area of the photosensitive surface of the embodiment of the present disclosure cannot be too large, which is a large area within the area range.

[0120] According to the embodiment of the present disclosure, the method can further include the following operations.

[0121] The total area of the same type of photosensitive surface is determined according to the tissue structure characteristics in the measurement region.

[0122] According to the embodiment of the present disclosure, the total area of the same type of photosensitive surface can be determined according to the tissue structure characteristics in the measurement region. Wherein the tissue structure characteristics can be understood as the structural characteristics possessed by the measurement region.

[0123] For example, if the measurement region is an area where three blood vessels intersect, and the same type of photosensitive surface is arranged in the area where three blood vessels intersect, the total area of the same type of photosensitive surface is limited by the area of the area where three blood vessels intersect, that is, the total area of the same type of photosensitive surface needs to be determined according to the area of the area where three blood vessels intersect.

[0124] For another example, if the measurement region is an area where a finger is located, and the same type of photosensitive surface is arranged in the area where the finger is located, the total area of the same type of photosensitive surface is limited by the area of the area where the finger is located, that is, the total area of the same type of photosensitive surface needs to be determined according to the area of the area where the finger is located.

[0125] It should be noted that, since the area of the photosensitive surface in the embodiment of the present disclosure can be determined according to the tissue structure characteristics, and the area determined according to the tissue structure characteristics is usually not too large, the area of the photosensitive surface in the embodiment of the present disclosure cannot be too large, which is a large area within the area range.

[0126] According to the embodiment of the present disclosure, the ratio of the area of each photosensitive surface to the circumference of the photosensitive surface is greater than or equal to a ratio threshold.

[0127] According to an embodiment of the present disclosure, in order to reduce the influence of jitter caused by the uncertainty of incident light transmission, the randomness of the light source, physiological background variation and pulse beat on the distribution of Raman scattered light on the measurement region, the reason for making the ratio of the area of the light-sensitive surface to the perimeter of the light-sensitive surface as large as possible is that.

[0128] For ease of illustration, the light-sensitive surface is divided into two parts, i.e., an edge part and a non-edge part (or an internal part). Generally, jitter mainly affects the Raman scattered light collected by the edge part, while the non-edge part is less affected, i.e., the non-edge part can more stably collect Raman scattered light. In another perspective, in the presence of jitter, the intensity distribution of Raman scattered light located in the edge part will change slightly, so the light intensity value of the Raman scattered light received by the edge part will change greatly. However, since the Raman scattered light located in the non-edge part can be more stably collected by the light-sensitive surface, the light intensity value of the Raman scattered light received by the non-edge part can remain relatively stable. Therefore, in order to effectively suppress the adverse effects of jitter on the measurement results, the ratio of the area corresponding to the non-edge part to the area of the light-sensitive surface can be made as large as possible. The larger the ratio, the better the effect of weakening the adverse effects. The edge part can be represented by the light-sensitive perimeter of the light-sensitive surface, and the non-edge part can be represented by the area of the light-sensitive surface. Therefore, the ratio of the area of the light-sensitive surface to the perimeter of the light-sensitive surface can be made as large as possible.

[0129] For example, the light-sensitive surface 1 is a circular light-sensitive surface, and the light-sensitive surface 2 is a square light-sensitive surface. In the case of the same light-sensitive perimeter, since the area of the light-sensitive surface 1 is larger than the area of the light-sensitive surface 2, the ratio of the area of the light-sensitive surface 1 to the perimeter is larger than the ratio of the area of the light-sensitive surface 2 to the perimeter. Therefore, the light-sensitive surface 1 has a better effect of weakening the adverse effects than the light-sensitive surface 2.

[0130] It should be noted that the ratio of the area of the light-sensitive surface to the perimeter of the light-sensitive surface being greater than or equal to the ratio threshold is explained under the condition that the area of the light-sensitive surface is greater than or equal to the area threshold. For most shapes of light-sensitive surfaces, if the ratio of the area of the light-sensitive surface to the perimeter of the light-sensitive surface is greater than or equal to the ratio threshold, the size of the area of the light-sensitive surface is actually also limited. This is because for most shapes of figures, the ratio of the area of the figure to the perimeter and the size of the area have a positive correlation, i.e., the larger the ratio of the area of the figure to the perimeter, the larger the area of the figure.

[0131] For example, a circle, the area of a circle is πR 2, the ratio of the area of the circle to the perimeter of the circle is R / 2, where R represents the radius. Since the ratio of the area of the circle to the perimeter of the circle is only related to the radius, the size of the area of the circle is only related to the radius, and thus the ratio of the area of the circle to the perimeter of the circle and the size of the area have a positive correlation, if the ratio of the area of the circle to the perimeter of the circle is limited, the size of the area of the circle is also limited. For example, a square, the area of the square is a 2 , the ratio of the area of the square to the perimeter of the square is a / 4, and a represents the side length. Since the ratio of the area of the square to the perimeter of the square is only related to the side length, the size of the area of the square is only related to the side length, and thus the ratio of the area of the square to the perimeter of the square and the size of the area have a positive correlation, if the ratio of the area of the square to the perimeter of the square is limited, the size of the area of the square is also limited.

[0132] According to an embodiment of the present disclosure, the ratio threshold is greater than or equal to 0.04 mm.

[0133] According to an embodiment of the present disclosure, the area of the photosensitive surface of the present disclosure is a relatively large area, that is, the area of the photosensitive surface is a large area in the area range. The following will be described in this case.

[0134] Firstly, the area of the photosensitive surface cannot be too small. Since the large-area photosensitive surface of the embodiment of the present disclosure refers to the area of the photosensitive surface that enables the photosensitive surface to collect the light intensity value of the Raman scattered light emitted by the exit position within the preset anti-shake range, the large area in the large-area photosensitive surface of the embodiment of the present disclosure is used to realize the large area of anti-shake, and since the area of the photosensitive surface that enables the photosensitive surface to collect the light intensity value of the Raman scattered light emitted by the exit position within the preset anti-shake range can be represented by the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface, and in general, the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface and the area of the photosensitive surface have a positive correlation, if the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to the ratio threshold, the size of the area of the photosensitive surface is actually limited, that is, the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface greater than or equal to the ratio threshold can also limit the area of the photosensitive surface cannot be too small.

[0135] Secondly, the area of the photosensitive surface cannot be too large. The embodiment of the present disclosure requires that the average optical path of the Raman scattered light received by the photosensitive surface in the target tissue layer accounts for a proportion greater than or equal to the proportion threshold of the total optical path, and / or the area of the photosensitive surface is determined according to the tissue structure characteristics, and the above description shows that the area of the photosensitive surface cannot be too large.

[0136] Therefore, it can be shown that the area of the photosensitive surface of the embodiment of the present disclosure is a relatively large area, that is, a large area in the area range.

[0137] In addition, there can be a case that although the area of the light-receiving surface is large, the ratio of the area of the light-receiving surface to the perimeter of the light-receiving surface is not large due to the large perimeter of the light-receiving surface, that is, the ratio of the area of the light-receiving surface to the perimeter of the light-receiving surface is less than the ratio threshold value, and thus the light-receiving surface with an absolute large area can also be difficult to meet the requirement of anti-shake. There can also be a case that the ratio of the area of the light-receiving surface to the perimeter of the light-receiving surface is less than the ratio threshold value due to the too small area of the light-receiving surface and the large perimeter of the light-receiving surface, and thus the too small area of the light-receiving surface is also difficult to meet the requirement of anti-shake.

[0138] According to an embodiment of the present disclosure, the light-receiving surface is in contact with or non-contact with the surface of the measurement region.

[0139] According to an embodiment of the present disclosure, the form of the tissue component measurement can include contact measurement and non-contact measurement. The contact measurement can avoid the interference light being received by the light-receiving surface, and thus can improve the possibility of obtaining a real measured tissue component signal. The non-contact measurement can avoid the influence of interference factors such as temperature and pressure on the measurement result, and thus can improve the possibility of obtaining a real measured tissue component signal.

[0140] If the light-receiving surface is set to be in contact with the surface of the measurement region, it can be considered that the form of the tissue component measurement is contact measurement. If the light-receiving surface is set to be non-contact with the surface of the measurement region, it can be considered that the form of the tissue component measurement is non-contact measurement.

[0141] According to an embodiment of the present disclosure, the distance between the light-receiving surface and the surface of the measurement region is less than or equal to a first distance threshold value, and the efficiency of the light-receiving surface in receiving the Raman scattered light is greater than or equal to an efficiency threshold value.

[0142] According to an embodiment of the present disclosure, since the light-receiving surface is made of a photosensitive material and the area of the light-receiving surface is continuous, a large range of light intensity values can be received, and the efficiency of receiving the Raman scattered light can be improved. Based on this, even in the case of being close to the surface of the measurement region, that is, in the case that the distance between the light-receiving surface and the surface of the measurement region is less than or equal to the first distance threshold value, the efficiency of receiving the Raman scattered light can be greater than or equal to the efficiency threshold value.

[0143] According to an embodiment of the present disclosure, each light-receiving surface includes a ring-shaped light-receiving surface or a non-ring-shaped light-receiving surface, and the shapes of different light-receiving surfaces are the same or different.

[0144] According to an embodiment of the present disclosure, each light-receiving surface can be made of a photosensitive material. The ring-shaped light-receiving surface can avoid the problem of azimuth positioning and can also achieve a large area design in a small source-probe distance range. It should be noted that since the source-probe distance is usually a relatively important physical quantity in the measurement of living tissue components, it is very meaningful to achieve a large area design in a small source-probe distance range.

[0145] According to the embodiments of the present disclosure, in some cases, the non-annular photosensitive surface has the following beneficial effects.

[0146] Firstly, since the measurement result is affected by the measurement area, generally, if the photosensitive surface is arranged in a measurement area conducive to measurement, the measurement result obtained by arranging the photosensitive surface in the measurement area conducive to measurement is better than that obtained by arranging the photosensitive surface in a measurement area interfering with measurement, and thus the photosensitive surface can be arranged at a suitable position according to the characteristics of the tissue structure. The non-annular photosensitive surface can more easily avoid the measurement area interfering with measurement, such as the blood vessel or wound area, and thus the non-annular photosensitive surface will have better effects.

[0147] Secondly, due to the non-uniformity of the tissue, the transmission path of the same incident light in the tissue can be different, and thus the average optical path corresponding to the Raman scattered light at different exit positions is different. Taking blood glucose as an example of the measured tissue component, generally, the dermis layer is the main source of the blood glucose signal, and thus it is required that the Raman scattered light is mainly Raman scattered light transmitted in the dermis layer, and accordingly, the average optical path corresponding to the Raman scattered light has certain requirements.

[0148] Suppose that the annular photosensitive surface of the corresponding size is designed according to the requirements of the average optical path, it can be considered that the average optical paths corresponding to the Raman scattered light received by different photosensitive positions of the annular photosensitive surface are basically similar and are mainly Raman scattered light through the dermis layer, and the average optical path is within the average optical path range C. In this case, if the skin tissue is uniform, the above conclusion is in line with the actual situation. However, since the skin tissue is generally not uniform, the average optical paths corresponding to the Raman scattered light received by different photosensitive positions of the same annular photosensitive surface are quite different, for example, the average optical paths corresponding to the Raman scattered light received by a part of the photosensitive positions of the annular photosensitive surface are basically similar and within the average optical path range C, and the average optical paths corresponding to the Raman scattered light received by another part of the photosensitive positions of the annular photosensitive surface are quite different from the foregoing and are not within the average optical path range C. Since the average optical path of the Raman scattered light within the average optical path range C indicates that the Raman scattered light is mainly Raman scattered light through the dermis layer, the Raman scattered light not within the average optical path range C can not be mainly Raman scattered light through the dermis layer, and the annular photosensitive surface outputs one Raman intensity, and thus in the case of non-uniform skin tissue, the signal quality of the Raman intensity obtained by using the annular photosensitive surface is not high, and thus the possibility of obtaining the real measured tissue component signal is affected.

[0149] The non-ring-shaped light sensing surface can be set according to actual conditions. Taking the above example as an example, assuming that the average optical path outside the average optical path range C is in the average optical path range D, two non-ring-shaped light sensing surfaces can be used, one of which is used to receive the light intensity value of the Raman scattering light with the average optical path in the average optical path range C, and the other is used to receive the light intensity value of the Raman scattering light with the average optical path in the average optical path range D. The Raman intensities of the two non-ring-shaped light sensing surfaces are consistent with the actual situation, which is beneficial to ensure the possibility of obtaining the real measured tissue composition signal.

[0150] Thirdly, when the tissue composition measurement is performed by using the time difference measurement method based on the pulse wave, the pulse signal needs to be fully utilized, that is, the difference between the systolic light intensity and the diastolic light intensity is made as large as possible. In the above case, since most of the ring-shaped light sensing surface does not locate above the blood vessel, the collection effect of the pulse signal is affected, and thus the difference between the systolic light intensity and the diastolic light intensity is reduced. Therefore, the difference between the systolic light intensity and the diastolic light intensity obtained by using the ring-shaped light sensing surface is smaller than the difference between the systolic light intensity and the diastolic light intensity obtained by using the non-ring-shaped light sensing surface.

[0151] Fourthly, due to the influence of tissue non-uniformity and physiological background variation on the Raman scattering light, the average optical path of the Raman scattering light received by different light sensing surfaces with the same source-probe distance from the center of the incident light may be different. Therefore, the Raman intensities collected by different light sensing surfaces with the same source-probe distance from the center of the incident light can be used for difference operation to perform tissue composition measurement. The above non-ring-shaped light sensing surface can be realized, that is, for the same source-probe distance, at least two non-ring-shaped light sensing surfaces can be discretely arranged with the center of the incident light as the center to output two Raman intensities.

[0152] Fifthly, the manufacturing process is less difficult, and the manufacturing cost is lower.

[0153] The following will be described in detail with reference to the accompanying drawings Figure 5 The fourth aspect will be described. Figure 5 A schematic diagram of a differential measurement according to an embodiment of the present disclosure is schematically shown. As shown in the figure, Figure 6 As shown, Figure 6 The center of the four fan ring light sensing surfaces is at the same distance from the center of the incident light, that is, has the same source-probe distance. Due to tissue non-uniformity, the average optical path of the Raman scattering light received by the fan ring light sensing surface 1 and the fan ring light sensing surface 2 is different, and thus the Raman intensities collected by the fan ring light sensing surface 1 and the fan ring light sensing surface 2 can be used for difference operation to realize differential measurement.

[0154] According to an embodiment of the present disclosure, the non-ring-shaped photosensitive surface includes a sector ring photosensitive surface, a circular photosensitive surface, a sector photosensitive surface, an elliptical photosensitive surface, or a polygon photosensitive surface.

[0155] According to an embodiment of the present disclosure, the polygon photosensitive surface includes a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

[0156] According to an embodiment of the present disclosure, the central angle can be designed according to actual conditions to obtain a corresponding sector ring photosensitive surface. For example, a sector ring photosensitive surface with a central angle of 90°, a sector ring photosensitive surface with a central angle of 180°, and a sector ring photosensitive surface with a central angle of 45°.

[0157] According to an embodiment of the present disclosure, the same type of photosensitive surface includes a ring-shaped photosensitive surface or a non-ring-shaped photosensitive surface, wherein the same type of photosensitive surface includes one or more photosensitive surfaces, and the same type of photosensitive surface is used to output one Raman intensity.

[0158] According to an embodiment of the present disclosure, the same type of photosensitive surface can be a ring-shaped photosensitive surface or a non-ring-shaped photosensitive surface, that is, from the whole, the same type of photosensitive surface presents a ring-shaped photosensitive surface or a non-ring-shaped photosensitive surface. According to the number of photosensitive surfaces included in the same type of photosensitive surface, it can be determined whether the shape presented from the whole is formed by one single photosensitive surface or formed by combination of multiple photosensitive surfaces. Wherein, the shape of each photosensitive surface in the same type of photosensitive surface can be a ring-shaped photosensitive surface or a non-ring-shaped photosensitive surface.

[0159] According to an embodiment of the present disclosure, the same type of photosensitive surface is a ring-shaped photosensitive surface, which can include: in the case that the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent ring-shaped photosensitive surface. In the case that the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a ring-shaped photosensitive surface formed by combination of multiple photosensitive surfaces. The same type of photosensitive surface is a non-ring-shaped photosensitive surface, which can include: in the case that the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-ring-shaped photosensitive surface. In the case that the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a non-ring-shaped photosensitive surface formed by combination of multiple photosensitive surfaces.

[0160] According to an embodiment of the present disclosure, the multiple photosensitive surfaces participating in combination are closely arranged to try to ensure that there is no gap between adjacent photosensitive surfaces. Since the circular photosensitive surface or the square photosensitive surface is relatively common at present, the manufacturing process is less difficult and the manufacturing cost is lower, while other shapes of photosensitive surfaces usually need to be customized, the manufacturing process is more difficult and the manufacturing cost is higher, therefore, if limited by the manufacturing cost, the combination method can be used to combine multiple circular photosensitive surfaces and / or multiple square photosensitive surfaces to form other shapes of the same type of photosensitive surface. Wherein, the square includes a square or a rectangle.

[0161] In addition, the cost of the photosensitive surface is related to the size of the photosensitive surface. Generally, the larger the photosensitive surface, the higher the manufacturing cost. If a large-area photosensitive surface is needed and multiple small-area photosensitive surfaces are available, the multiple small-area photosensitive surfaces can be combined to obtain a large-area photosensitive surface to reduce the manufacturing cost.

[0162] According to an embodiment of the present disclosure, when it is determined that the distance between the photosensitive surface of the same type and the target site is greater than or equal to the second distance threshold, the photosensitive surface of the same type includes a ring-shaped photosensitive surface, a fan ring-shaped photosensitive surface, a fan-shaped photosensitive surface, a circular photosensitive surface, or a square photosensitive surface.

[0163] According to an embodiment of the present disclosure, when it is determined that the distance between the photosensitive surface of the same type and the target site is greater than or equal to the second distance threshold, the photosensitive surface of the appropriate shape can be selected according to the jitter of the actual Raman scattering light to weaken the adverse effects of the jitter on the measurement to the greatest extent.

[0164] The target site can be the site where the jitter occurs. Since one of the sources of the jitter is the pulse, and the pulse is related to the blood vessel, the target site can be the blood vessel. Generally, the jitter distribution of the Raman scattering light close to the blood vessel has a certain directionality, and the jitter distribution of the Raman scattering light far from the blood vessel is relatively uniform and has no directionality.

[0165] If the photosensitive surface of the same type is far from the target site (for example, the target blood vessel), it can be indicated that the jitter distribution of the Raman scattering light is relatively uniform, and in this case, the ring-shaped photosensitive surface, the fan ring-shaped photosensitive surface, the fan-shaped photosensitive surface, the circular photosensitive surface, or the square photosensitive surface can be selected. The photosensitive surface of the same type far from the target site can be understood as the distance between each photosensitive surface of the photosensitive surface of the same type and the target site being greater than or equal to the second distance threshold. The distance between each photosensitive surface of the photosensitive surface of the same type and the target site being greater than or equal to the second distance threshold can include the distance between the edge of the photosensitive surface closest to the target site and the target site being greater than or equal to the second distance threshold, or the photosensitive surface of the same type not being in contact with the target site, and the distance between the center of the photosensitive surface closest to the target site and the target site being greater than or equal to the second distance threshold.

[0166] In the case where the photosensitive surface of the same type is far from the target site, if the average optical path of the Raman scattering light received by different photosensitive positions of each photosensitive surface of the photosensitive surface of the same type is less than or equal to the optical path threshold, it can be indicated that the jitter of the Raman scattering light is affected by the size of the optical path, that is, the greater the average optical path of the Raman scattering light, the more obvious the jitter of the Raman scattering light, and vice versa. In this case, the longer the arc length corresponding to the position farther from the center of the incident light can be designed, and thus the ring-shaped photosensitive surface, the fan ring-shaped photosensitive surface, or the fan-shaped photosensitive surface can be selected.

[0167] In the case that the same type of photosensitive surface is away from the target part, if the average optical path of the Raman scattered light received by different photosensitive positions of each photosensitive surface in the same type of photosensitive surface is greater than the optical path threshold, it can be explained that the jitter of the Raman scattered light is almost irrelevant to the size of the optical path. In this case, a circular photosensitive surface or a square photosensitive surface can be selected.

[0168] According to an embodiment of the present disclosure, in the case that the same type of photosensitive surface is a fan ring photosensitive surface, if the same type of photosensitive surface includes one photosensitive surface, the fan ring photosensitive surface is an independent fan ring photosensitive surface. If the same type of photosensitive surface includes multiple photosensitive surfaces, the fan ring photosensitive surface is a photosensitive surface formed by combining multiple photosensitive surfaces. Similarly, for the case that the same type of photosensitive surface includes a ring photosensitive surface, a circular photosensitive surface, a square photosensitive surface or a fan photosensitive surface, the same type of photosensitive surface can be an independently formed same type of photosensitive surface or a combined same type of photosensitive surface.

[0169] It should be noted that, since the circular photosensitive surface or the square photosensitive surface is relatively common at present, the manufacturing process is less difficult and the manufacturing cost is lower, while other shapes of photosensitive surfaces usually need to be customized, the manufacturing process is more difficult and the manufacturing cost is higher. Therefore, if limited by the manufacturing cost, in the case that it is determined that the distance between the same type of photosensitive surface and the target part is greater than or equal to the first distance threshold, the same type of photosensitive surface includes a circular photosensitive surface or a square photosensitive surface.

[0170] According to an embodiment of the present disclosure, in the case that it is determined that the distance between the same type of photosensitive surface and the target part is less than or equal to the third distance threshold, the shape of the same type of photosensitive surface is determined according to the jitter distribution of the Raman scattered light.

[0171] According to an embodiment of the present disclosure, if the same type of photosensitive surface is close to the target part (for example, the target blood vessel), it can be explained that the jitter distribution of the Raman scattered light has a certain directionality. In this case, the shape of the same type of photosensitive surface can be determined according to the jitter distribution of the Raman scattered light, and optionally, the shape of the same type of photosensitive surface is a similar figure of the jitter distribution of the Raman scattered light. For example, if the jitter distribution of the Raman scattered light is an elliptical shape, the shape of the same type of photosensitive surface can be designed as an elliptical photosensitive surface. Or, if the jitter distribution of the Raman scattered light is a rectangular shape, the shape of the same type of photosensitive surface can be designed as a rectangular photosensitive surface. Or, if the jitter distribution of the Raman scattered light is a rhombus, the shape of the same type of photosensitive surface can be designed as a rhombus photosensitive surface.

[0172] According to an embodiment of the present disclosure, the jitter distribution of the Raman scattered light comprises a decomposition into a jitter distribution along a first direction and a jitter distribution along a second direction, the first direction and the second direction being perpendicular to each other, a ratio of a length of the same kind of photosensitive surface along the first direction to a length of the same kind of photosensitive surface along the second direction being determined according to a ratio of a jitter amplitude of the Raman scattered light along the first direction to a jitter amplitude of the Raman scattered light along the second direction, the jitter amplitude of the Raman scattered light along the first direction being the largest.

[0173] According to an embodiment of the present disclosure, if the jitter distribution of the Raman scattered light comprises jitter distributions of the Raman scattered light along two perpendicular directions, wherein the jitter distributions of the two perpendicular directions are obtained by decomposing the jitter of the Raman scattered light into the two perpendicular directions, the two perpendicular directions are respectively referred to as a first direction and a second direction, and the jitter amplitude of the Raman scattered light along the first direction is the largest, then the ratio of the length of the same kind of photosensitive surface along the first direction to the length of the same kind of photosensitive surface along the second direction can be set according to the ratio of the jitter amplitude of the Raman scattered light along the first direction to the jitter amplitude of the Raman scattered light along the second direction, so that the ratio of the length of the same kind of photosensitive surface along the first direction to the length of the same kind of photosensitive surface along the second direction is greater than or equal to the ratio of the jitter amplitude of the Raman scattered light along the first direction to the jitter amplitude of the Raman scattered light along the second direction.

[0174] For example, if the first direction and the second direction are respectively the Y-axis direction and the X-axis direction in a rectangular coordinate system, then the ratio of the jitter amplitude of the Raman scattered light along the Y-axis direction to the jitter amplitude of the Raman scattered light along the X-axis direction can be represented as The ratio of the length of the same kind of photosensitive surface along the Y-axis direction to the length of the same kind of photosensitive surface along the X-axis direction can be represented as

[0175] According to an embodiment of the present disclosure, the same kind of photosensitive surface comprises a rectangular photosensitive surface or an elliptical photosensitive surface, the ratio of the length to the width of the rectangular photosensitive surface being determined according to the ratio of the jitter amplitude of the Raman scattered light along the first direction to the jitter amplitude of the Raman scattered light along the second direction, and the ratio of the major axis to the minor axis of the elliptical photosensitive surface being determined according to the ratio of the jitter amplitude of the Raman scattered light along the first direction to the jitter amplitude of the Raman scattered light along the second direction.

[0176] ​According to an embodiment of the present disclosure, if the distance from the target site to the same kind of photosensitive surface is less than or equal to the third distance threshold, the jitter distribution of the Raman scattered light includes a jitter distribution along a first direction and a jitter distribution along a second direction, the first direction and the second direction are perpendicular to each other, and the same kind of photosensitive surface can include a rectangular photosensitive surface or an elliptical photosensitive surface. Wherein, the ratio of the length to the width of the rectangular photosensitive surface is greater than or equal to the ratio of the jitter amplitude of the Raman scattered light along the first direction to the jitter amplitude along the second direction. The ratio of the major axis to the minor axis of the elliptical photosensitive surface is greater than or equal to the ratio of the jitter amplitude of the Raman scattered light along the first direction to the jitter amplitude along the second direction.

[0177] According to an embodiment of the present disclosure, determining the concentration of the measured tissue component according to at least one Raman intensity corresponding to the second preset wavelength can include the following operations.

[0178] Determining the concentration of the measured tissue component based on the interference suppression method processing at least one Raman intensity corresponding to the second preset wavelength.

[0179] According to an embodiment of the present disclosure, since the variation of the uncontrollable measurement condition has the characteristics of being unpredictable and uncontrollable, it is difficult to ensure the reproducibility of such measurement conditions by using effective control methods, thereby reducing the influence of the variation of the uncontrollable measurement condition on the measurement result. But a reasonable mathematical algorithm can be used to reduce the influence of the variation of the uncontrollable measurement condition on the measurement result, so that its influence on the measurement result can be reduced to a negligible level, that is, the influence of the variation of the uncontrollable measurement condition on the measurement result is equivalent to the influence of random noise on the measurement result.

[0180] In order to reduce the influence of the variation of the uncontrollable measurement condition on the measurement result, an interference suppression method can be used, wherein the interference suppression method can include a differential measurement method. The differential measurement method can include a time differential measurement method and a position differential measurement method.

[0181] According to an embodiment of the present disclosure, determining the concentration of the measured tissue component based on the interference suppression method processing at least one Raman intensity corresponding to the second preset wavelength can include the following operations.

[0182] From at least two Raman intensities corresponding to the second preset wavelength, a first Raman intensity and a second Raman intensity are determined. The first Raman intensity and the second Raman intensity corresponding to the second preset wavelength are differentially processed to obtain a differential signal. According to the differential signal corresponding to the second preset wavelength, the concentration of the measured tissue component is determined.

[0183] According to an embodiment of the present disclosure, the differential measurement method can reduce the influence of the variation of uncontrollable measurement conditions on the measurement result because, if the interference information carried by the Raman intensities at different average optical paths is basically the same, the effective information carried by the Raman intensities at different average optical paths is different, and therefore the Raman intensities at two average optical paths (the first Raman intensity and the second Raman intensity) can be differentially processed to obtain a differential signal, and the concentration of the measured tissue component is determined according to the differential signal. The interference information can be understood as the response of the Raman intensity to the interference. The effective information can be understood as the response of the Raman intensity to the measured tissue component.

[0184] According to an embodiment of the present disclosure, the differential processing in the differential processing of the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength can include a hardware aspect processing mode and a software aspect processing mode. The hardware aspect processing mode can include processing by using a differential circuit. The software aspect processing mode can include differential operation by using a differential algorithm. The differential algorithm can include direct differential operation and logarithmic differential operation. The direct differential operation means directly subtracting two parameters. The logarithmic differential operation means first taking logarithm of two parameters to obtain the logarithmic parameters, and then subtracting the two logarithmic parameters.

[0185] According to an embodiment of the present disclosure, the differential operation method can effectively weaken the common-mode interference information, and further improve the possibility of obtaining the real measured tissue component signal.

[0186] According to an embodiment of the present disclosure, the differential processing of the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength to obtain the differential signal can include the following operations.

[0187] The first Raman intensity and the second Raman intensity corresponding to the second preset wavelength are processed by using a differential circuit to obtain the differential signal.

[0188] According to an embodiment of the present disclosure, a differential circuit can be used to realize the differential processing of the first Raman intensity and the second Raman intensity to directly obtain the differential signal.

[0189] According to an embodiment of the present disclosure, the differential processing of the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength to obtain the differential signal can include the following operations.

[0190] The first Raman intensity and the second Raman intensity corresponding to the second preset wavelength are processed by using a differential algorithm to obtain the differential signal.

[0191] According to an embodiment of the present disclosure, the differential processing of the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength to obtain the differential signal can include the following operations.

[0192] The first Raman intensity and the second Raman intensity corresponding to the preset wavelength are directly difference operated to obtain a difference signal.

[0193] According to an embodiment of the present disclosure, the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength are processed by using a difference algorithm to obtain a difference signal, which can include the following operations.

[0194] The first Raman scattering light intensity and the second Raman scattering light intensity corresponding to the second preset wavelength are logarithm processed to obtain a first logarithm light intensity and a second logarithm light intensity. The first logarithm light intensity and the second logarithm light intensity corresponding to the second preset wavelength are difference operated to obtain a difference signal.

[0195] According to an embodiment of the present disclosure, the first logarithm light intensity represents a logarithm of the first Raman intensity, and the second logarithm light intensity represents a logarithm of the second Raman intensity.

[0196] The difference signal can be determined by the following formula (1).

[0197]

[0198] wherein, A D represents the difference signal, represents the first Raman intensity, represents the second Raman intensity. represents an average optical path corresponding to the first Raman intensity, represents an average optical path corresponding to the second Raman intensity.

[0199] According to an embodiment of the present disclosure, the first Raman intensity and the second Raman intensity are collected by the same or different same type of photosensitive surfaces at different times, wherein the first Raman intensity is a systolic light intensity, the second Raman intensity is a diastolic light intensity, the same type of photosensitive surface includes one or more photosensitive surfaces, and the same type of photosensitive surface is used to output one Raman intensity.

[0200] According to an embodiment of the present disclosure, in the case that the first Raman intensity and the second Raman intensity are collected by the same or different same type of photosensitive surfaces at different times, a time difference measurement method based on a pulse wave can be used for tissue composition measurement.

[0201] The pulse is the arterial pulsation, which refers to the periodic contraction and relaxation with the beating of the heart. The pressure in the aorta causes the diameter of the blood vessel to pulsate, and the blood flow in the blood vessel also changes regularly and periodically. Each pulse waveform includes a rising branch and a falling branch, wherein the rising branch represents the expansion of the artery in the systolic period, and the falling branch represents the retraction of the artery in the diastolic period. One systolic and diastolic period represents one pulsation cycle.

[0202] According to an embodiment of the present disclosure, since the time differential measurement method based on the pulse wave is adopted, the information of the pulse needs to be utilized as much as possible, and therefore, in order to improve the possibility of obtaining the real measured tissue component signal, the photosensitive surface can be arranged as close to the target part (for example, the target blood vessel) as possible. That is, the same photosensitive surface for outputting the first Raman intensity and the second Raman intensity can be arranged at a position with a distance from the target part less than or equal to a fourth distance threshold. The fourth distance threshold can be zero, that is, the same photosensitive surface can be arranged on the target part. The same photosensitive surface for outputting the first Raman intensity and the second Raman intensity is arranged at a position with a distance from the target part less than or equal to the fourth distance threshold, that is, each photosensitive surface in the same photosensitive surface for outputting the first Raman intensity and the second Raman intensity has a distance from the target part less than or equal to the fourth distance threshold. The distance from each photosensitive surface in the same photosensitive surface to the target part less than or equal to the fourth distance threshold can be that the distance from the edge of the photosensitive surface farthest from the target part to the target blood vessel is less than or equal to the fourth distance threshold.

[0203] It should be noted that the time differential measurement method based on the pulse wave needs to utilize the information of the pulse as much as possible, which is not contradictory to the above-mentioned adoption of the large-area photosensitive surface to reduce the adverse effects of the pulse beat on the measurement. The former utilizes the useful information brought by the pulse beat as much as possible, and the latter reduces the adverse effects of the pulse beat as much as possible. In addition, the first Raman intensity can also be the diastolic light intensity, and the second Raman intensity can also be the systolic light intensity. The first Raman intensity and the second Raman intensity corresponding to the preset wavelength can be the Raman intensities in the same pulsation period, or the Raman intensities in different pulsation periods.

[0204] According to an embodiment of the present disclosure, the first Raman intensity corresponding to the second preset wavelength is collected by the first same photosensitive surface corresponding to the second preset wavelength, and the second Raman intensity corresponding to the second preset wavelength is collected by the second same photosensitive surface corresponding to the second preset wavelength, wherein the first same photosensitive surface includes one or more photosensitive surfaces, and the second same photosensitive surface includes one or more photosensitive surfaces.

[0205] According to an embodiment of the present disclosure, for the second preset wavelength, there is the first same photosensitive surface corresponding to the second preset wavelength and the second same photosensitive surface corresponding to the second preset wavelength, wherein the first same photosensitive surface is used to output the first Raman intensity corresponding to the second preset wavelength, and the second same photosensitive surface is used to output the second Raman intensity corresponding to the second preset wavelength. The first same photosensitive surface and the second same photosensitive surface can each include one or more photosensitive surfaces.

[0206] According to an embodiment of the present disclosure, the first Raman intensity and the second Raman intensity can be processed by using the position differential measurement method to determine the concentration of the measured tissue component.

[0207] According to an embodiment of the present disclosure, since the position differential measurement method is adopted to avoid the target site (e.g., the target blood vessel) as much as possible, in order to improve the possibility of obtaining the real measured tissue component signal, the photosensitive surface can be arranged as far away from the target site as possible. That is, the first same type of photosensitive surface for outputting the first Raman intensity can be arranged at a position with a distance greater than or equal to a fifth distance threshold from the target site, that is, each photosensitive surface in the first same type of photosensitive surface has a distance greater than or equal to the fifth distance threshold from the target site. The distance from the edge of the photosensitive surface closest to the target site in the first same type of photosensitive surface to the target site is greater than or equal to the fifth distance threshold. Alternatively, the first same type of photosensitive surface is not in contact with the target site, and the distance from the center of the photosensitive surface closest to the target site in the first same type of photosensitive surface to the target site is greater than or equal to the fifth distance threshold. The photosensitive surface for outputting the second Raman intensity is arranged at a position with a distance greater than or equal to a sixth distance threshold from the target site. For the understanding of the second same type of photosensitive surface for outputting the second Raman intensity arranged at a position with a distance greater than or equal to the sixth distance threshold from the target site, please refer to the description of the first same type of photosensitive surface for outputting the first Raman intensity, which will not be repeated here.

[0208] According to an embodiment of the present disclosure, the first same type of photosensitive surface and the second same type of photosensitive surface are the same type of photosensitive surface, and the Raman scattered light received by the first same type of photosensitive surface and the second same type of photosensitive surface is obtained by transmission of incident light from different incident positions.

[0209] According to an embodiment of the present disclosure, the first same type of photosensitive surface and the second same type of photosensitive surface are different types of photosensitive surfaces.

[0210] According to an embodiment of the present disclosure, since the incident position of the incident light can include at least one, if the incident position of the incident light includes at least two, the first same type of photosensitive surface and the second same type of photosensitive surface can be the same photosensitive surface, except that if the same type of photosensitive surface is used as the same type of photosensitive surface for receiving the Raman scattered light corresponding to the first Raman intensity, that is, as the first same type of photosensitive surface, the incident position of the Raman scattered light is the first incident position. If the same type of photosensitive surface is used as the same type of photosensitive surface for receiving the Raman scattered light corresponding to the second Raman intensity, that is, as the second same type of photosensitive surface, the incident position of the Raman scattered light is the second incident position, and the first incident position and the second incident position are different incident positions.

[0211] According to an embodiment of the present disclosure, the first same type of photosensitive surface and the second same type of photosensitive surface can also be different types of photosensitive surfaces.

[0212] According to an embodiment of the present disclosure, the average optical path of the Raman scattered light received by different sensing positions of each sensing surface of the first same type of sensing surface belongs to a first average optical path range, wherein the first average optical path range is determined according to a first average optical path value, and the first average optical path value is an average value calculated according to the average optical path of the Raman scattered light received by each sensing position of the first same type of sensing surface. The average optical path of the Raman scattered light received by different sensing positions of each sensing surface of the second same type of sensing surface belongs to a second average optical path range, wherein the second average optical path range is determined according to a second average optical path value, and the second average optical path value is an average value calculated according to the average optical path of the Raman scattered light received by each sensing position of the second same type of sensing surface.

[0213] According to an embodiment of the present disclosure, in order to improve the possibility of obtaining a true measured tissue component signal by using a position difference measurement method for tissue component measurement, it is necessary to ensure that the Raman scattered light received by the first same type of sensing surface has the characteristic of near optical path, and the Raman scattered light received by the second same type of sensing surface also has the characteristic of near optical path. Near optical path can be understood as the average optical path of the Raman scattered light within the average optical path range.

[0214] For the first same type of sensing surface, the average optical path of the Raman scattered light received by different sensing positions of each sensing surface of the first same type of sensing surface belongs to a first average optical path range. The first average optical path range is determined in the following manner. A first average optical path value of the average optical path of the Raman scattered light received by each sensing position of the first same type of sensing surface is determined, and a first optical path variation amplitude is determined. According to the first average optical path value and the first optical path variation amplitude, the first average optical path range is determined. For example, if the first average optical path value is b and the first optical path variation amplitude is ±40%, the first average optical path range can be greater than or equal to 0.6b and less than or equal to 1.4b.

[0215] For the second same type of sensing surface, the average optical path of the Raman scattered light received by different sensing positions of each sensing surface of the second same type of sensing surface belongs to a second average optical path range. The second average optical path range is determined in the following manner. A second average optical path value of the average optical path of the Raman scattered light received by each sensing position of the second same type of sensing surface is determined, and a second optical path variation amplitude is determined. According to the second average optical path value and the second optical path variation amplitude, the second average optical path range is determined.

[0216] According to an embodiment of the present disclosure, the absolute value of the difference between the first average optical path value and the second average optical path value belongs to a first optical path difference range.

[0217] According to an embodiment of the present disclosure, in order to improve the possibility of obtaining a true measured tissue component signal by measuring the tissue component based on the differential measurement method, the first same type of photosensitive surface and the second same type of photosensitive surface need to be arranged within a reasonable position range. The following will be described by taking blood glucose as an example. For the measured tissue component being blood glucose, the target tissue layer is the dermis layer, and the Raman intensity is required to be the Raman intensity mainly carrying the tissue component information in the dermis layer.

[0218] Firstly, if the position of the photosensitive surface is too close to the center of the incident light, the Raman intensity of the Raman scattered light will mainly carry the tissue component information in the epidermis layer. If the position of the photosensitive surface is too far from the center of the incident light, the Raman intensity of the Raman scattered light will mainly carry the tissue component information in the subcutaneous fat layer. The dermis layer is located between the epidermis layer and the subcutaneous fat layer. Therefore, the arrangement positions of the first same type of photosensitive surface and the second same type of photosensitive surface need to be selected within a reasonable position range, and the distance between the first same type of photosensitive surface and the second same type of photosensitive surface cannot be too large.

[0219] Secondly, although the differential measurement method can effectively weaken the common-mode interference, the differential measurement method will also lose part of the effective information, i.e., the blood glucose information, while weakening the common-mode interference. If the two positions are extremely close, the effective information can be completely lost. Therefore, the arrangement positions of the first same type of photosensitive surface and the second same type of photosensitive surface need to be selected within a reasonable position range, and the distance between the first same type of photosensitive surface and the second same type of photosensitive surface cannot be too small.

[0220] In order to arrange the first same type of photosensitive surface and the second same type of photosensitive surface within a reasonable position range, the arrangement positions of the first same type of photosensitive surface and the second same type of photosensitive surface can be determined according to an effective information measurement principle, a differential measurement precision optimization principle, and an interference signal effective elimination principle. The effective information measurement principle can mean that the Raman scattered light at the two positions can carry as much tissue component information in the target tissue layer as possible. Therefore, the two positions should be within a reasonable position range. The differential measurement precision optimization principle can mean that the two positions should have a certain distance to ensure that as much effective information as possible is retained after the differential. The interference signal effective elimination principle can mean that the distance between the two positions should be as small as possible to improve the effect of eliminating the common-mode interference by the differential measurement method.

[0221] Arranging the first same type of photosensitive surface and the second same type of photosensitive surface within a reasonable position range reflects that the absolute value of the difference between the first optical path average value corresponding to the first same type of photosensitive surface and the second optical path average value corresponding to the second same type of photosensitive surface belongs to the first optical path difference range. The first optical path difference range is determined according to the optimal differential optical path. The optimal differential optical path can be determined according to at least one of the above three principles.

[0222] It can be understood that the position setting requirement of the first same type photosensitive surface and the second same type photosensitive surface also requires that the area of the photosensitive surface cannot be too large, otherwise it will affect the differential effect, and further affect the possibility of obtaining the real measured tissue component signal.

[0223] According to an embodiment of the present disclosure, the first average optical path range is less than or equal to the first optical path difference range, and the second average optical path range is less than or equal to the first optical path difference range.

[0224] According to an embodiment of the present disclosure, in order to achieve the first same type photosensitive surface and the second same type photosensitive surface within a reasonable position range, it is also necessary to ensure that the first average optical path range is less than or equal to the first optical path difference range, and the second average optical path range is less than or equal to the first optical path difference range. Therefore, the absolute value of the difference between the first optical path average value corresponding to the first same type photosensitive surface and the second optical path average value corresponding to the second same type photosensitive surface belongs to the first optical path difference range, the first average optical path range is less than or equal to the first optical path difference range, and the second average optical path range is less than or equal to the first optical path difference range.

[0225] According to an embodiment of the present disclosure, the first optical path difference range is determined according to the optimal differential optical path corresponding to the second preset wavelength.

[0226] According to an embodiment of the present disclosure, in the case of determining the measurement region of the measured object, there is an optimal differential sensitivity corresponding to the second preset wavelength, wherein the optimal differential sensitivity can represent the sensitivity when the change of the differential signal caused by the unit change of the measured tissue component concentration is the largest, and the optimal differential optical path can be determined according to the optimal differential sensitivity, that is, the optimal differential optical path can be determined according to the differential measurement precision optimization principle. Therefore, the optical path corresponding to the optimal differential sensitivity is called the optimal differential optical path.

[0227] According to an embodiment of the present disclosure, after determining the optimal differential optical path corresponding to the second preset wavelength, an up-down adjustment range can be set, and the first optical path difference range corresponding to the second preset wavelength can be determined according to the optimal differential optical path corresponding to the second preset wavelength and the up-down adjustment range.

[0228] According to an embodiment of the present disclosure, the source-probe distance of each photosensitive surface in the first same type photosensitive surface corresponding to the second preset wavelength from the center of the incident light is within a preset source-probe distance range corresponding to the second preset wavelength, wherein the preset source-probe distance range is determined according to the source-probe distance of the floating reference position from the center of the incident light corresponding to the second preset wavelength.

[0229] According to an embodiment of the present disclosure, in order to further improve the possibility of obtaining the real measured tissue component signal, the position of the photosensitive surface can be set based on the floating reference method. Wherein, the floating reference method is described as follows.

[0230] For the measured object, when the incident light enters the tissue, absorption and scattering occur. The absorption directly causes the light energy to attenuate, and the scattering affects the distribution of the Raman scattered light by changing the direction of the photon transmission. The distribution of the Raman scattered light is the result of the combined effects of the absorption and the scattering. Based on the floating reference method, for the measured tissue composition, there is a position from the center of the incident light, at which the effects of the absorption and the scattering on the Raman intensity of the Raman scattered light are the same but in opposite directions, thus leading to the Raman scattered light being insensitive to the concentration change of the measured tissue composition. The position with the above characteristics can be referred to as a reference position (or a reference location). The Raman intensity of the Raman scattered light at the reference position reflects the response to the other interference than the measured tissue composition during the measurement. Meanwhile, for the measured tissue composition, there is also a position from the center of the incident light, at which the sensitivity of the Raman intensity of the Raman scattered light to the concentration change of the measured tissue composition is greater than or equal to a sensitivity threshold. The position with the above characteristics can be referred to as a measurement position. The Raman intensity of the Raman scattered light at the measurement position reflects the response to the measured tissue composition during the measurement, as well as the response to the other interference than the measured tissue composition. Moreover, the reference position and the measurement position are different due to the wavelength, the measured object, and the measurement region, and thus the reference position can be referred to as a floating reference position.

[0231] According to the embodiments of the present disclosure, since the Raman intensity of the Raman scattered light emitted at the floating reference position mainly carries the response to the other interference than the measured tissue composition during the measurement, the Raman intensity of the Raman scattered light emitted at the floating reference position can be introduced into the differential measurement to weaken the common-mode interference to the greatest extent and to lose the effective information to a lesser extent. Based on the above, in the case of determining the measurement region of the measured object, for the second preset wavelength, at least one photosensitive surface in the M photosensitive surfaces has a source-probe distance from the center of the incident light within a preset source-probe distance range corresponding to the second preset wavelength, and the preset source-probe distance range is determined according to the source-probe distance of the floating reference position corresponding to the second preset wavelength from the center of the incident light. In the embodiments of the present disclosure, the source-probe distance of each photosensitive surface in the first same type of photosensitive surface from the center of the incident light can be within the preset source-probe distance range corresponding to the second preset wavelength.

[0232] For example, for the measurement region B of the measured object A, the distance of the floating reference position corresponding to the second preset wavelength λ1 from the center of the incident light is 1.7 mm, and thus the preset source-probe distance range corresponding to the second preset wavelength λ1 can be 1.5 mm-1.9 mm.

[0233] Based on the above, the same type of photosensitive surface corresponding to the reference position and the same type of photosensitive surface corresponding to the measurement position can be determined. The Raman intensity collected by the same type of photosensitive surface corresponding to the reference position is referred to as the first Raman intensity, and the Raman intensity collected by the same type of photosensitive surface corresponding to the measurement region is referred to as the second Raman intensity. Alternatively, the Raman intensity collected by the same type of photosensitive surface corresponding to the measurement region is referred to as the first Raman intensity, and the Raman intensity collected by the same type of photosensitive surface corresponding to the reference position is referred to as the second Raman intensity.

[0234] According to an embodiment of the present disclosure, determining the concentration of the measured tissue component according to the at least one Raman intensity corresponding to the second preset wavelength can include the following operations.

[0235] The third Raman intensity is determined from the at least one Raman intensity corresponding to the second preset wavelength. The concentration of the measured tissue component is determined according to the third Raman intensity corresponding to the second preset wavelength.

[0236] According to an embodiment of the present disclosure, a non-differential measurement method can be used for tissue component measurement, i.e., the concentration of the measured tissue component is determined according to the third Raman intensity corresponding to the second preset wavelength.

[0237] According to an embodiment of the present disclosure, the third Raman intensity corresponding to the second preset wavelength is collected by the same type of photosensitive surface corresponding to the second preset wavelength. The difference between the average optical path of the Raman scattered light received by each photosensitive surface in the same type of photosensitive surface and the optimal optical path corresponding to the second preset wavelength belongs to the second optical path difference range.

[0238] According to an embodiment of the present disclosure, in order to improve the possibility of obtaining the real measured tissue component signal, in the case of determining the measurement region of the measured object, for the second preset wavelength, the average optical path of the Raman scattered light received by the different photosensitive positions in the same type of photosensitive surface used to collect the third Raman intensity is close to the optimal optical path corresponding to the second preset wavelength, i.e., the absolute value of the difference between the average optical path of the Raman scattered light received by the different photosensitive positions in the same type of photosensitive surface used to collect the third Raman intensity and the optimal optical path corresponding to the second preset wavelength is less than or equal to the second optical path difference range. The optimal optical path corresponding to the second preset wavelength can be understood as the optical path corresponding to the maximum sensitivity of the measured tissue component under the second preset wavelength.

[0239] According to an embodiment of the present disclosure, each Raman intensity is processed according to the light intensity value of the Raman scattered light collected by one or more photosensitive surfaces, which can include the following operations.

[0240] The one or more photosensitive surfaces are combined to output one Raman intensity. In the case that each of the one or more photosensitive surfaces is used individually, the light intensity values of the Raman scattered light collected by each of the photosensitive surfaces are calculated to obtain one Raman intensity.

[0241] According to an embodiment of the present disclosure, the photosensitive surfaces used to output one Raman intensity are referred to as the same type of photosensitive surfaces, and the same type of photosensitive surfaces can include one or more photosensitive surfaces. In this case, the condition that the different photosensitive surfaces are combined can be that the average optical path of the Raman scattered light received by each of the photosensitive surfaces is within an average optical path range. The average optical path range can be a range composed of a first average optical path threshold value and a second average optical path threshold value. The first average optical path threshold value and the second average optical path threshold value can be determined according to an average optical path value and an optical path variation amplitude.

[0242] The photosensitive surface is usually used in cooperation with an amplification circuit corresponding to the photosensitive surface to output one light intensity value. In order to enable the same type of photosensitive surfaces to output a more accurate Raman intensity, the product of the light response rate of each of the photosensitive surfaces in the same type of photosensitive surfaces and the amplification factor of the amplification circuit used in cooperation with the photosensitive surface needs to be a preset value. In the case that the light response rate of each of the photosensitive surfaces and the amplification factor of the amplification circuit used in cooperation with the photosensitive surface are ensured to be the same preset value, the same type of photosensitive surfaces outputs one Raman intensity. If the product of the light response rate of the photosensitive surface and the amplification factor of the amplification circuit used in cooperation with the photosensitive surface is not the same preset value, a corresponding method needs to be adopted to make the product the preset value.

[0243] The same type of photosensitive surfaces outputting one Raman intensity can be implemented in a hardware or software manner.

[0244] Method one, hardware manner. The cathodes of the different photosensitive surfaces in the same type of photosensitive surfaces can be electrically connected to each other and the anodes of the different photosensitive surfaces can be electrically connected to each other, that is, the different photosensitive surfaces are electrically connected in common cathode and common anode. In this case, the different photosensitive surfaces are connected in parallel, and one or more photosensitive surfaces are combined to output one Raman intensity. It should be noted that the light response rates of the different photosensitive surfaces need to be as consistent as possible to obtain a more accurate Raman intensity.

[0245] Method two, software manner. The cathodes of the different photosensitive surfaces in the same type of photosensitive surfaces are not connected to each other and the anodes of the different photosensitive surfaces are not connected to each other, that is, each of the photosensitive surfaces is used individually to output one light intensity value. After obtaining the light intensity values corresponding to each of the photosensitive surfaces, a corresponding algorithm can be used to weight and sum the light intensity values of each of the photosensitive surfaces in the same type of photosensitive surfaces to obtain one Raman intensity.

[0246] Optionally, the Raman intensity corresponding to the same kind of photosensitive surface can be determined by the following formulas (2) and (3).

[0247]

[0248] wherein I represents the Raman intensity corresponding to the same kind of photosensitive surface, I i represents the light intensity value corresponding to the photosensitive surface i, i∈{1, 2, …, N-1, N}, N represents the number of photosensitive surfaces included in the same kind of photosensitive surface, 1≤N≤M, M represents the total number of photosensitive surfaces, a i represents the weighting coefficient corresponding to the photosensitive surface i, H represents a preset value, b i represents the light response rate corresponding to the photosensitive surface i, g i represents the amplification multiple of the amplification circuit used in cooperation with the photosensitive surface i.

[0249] According to the embodiment of the present disclosure, irradiating the measurement region with incident light of the first preset wavelength can include the following operations.

[0250] In the case of meeting the reproducibility of the controllable measurement condition, irradiating the measurement region with incident light of the first preset wavelength.

[0251] According to the embodiment of the present disclosure, in the process of measuring the tissue component, the variation of the measurement condition can overwhelm the weak tissue component signal, making it difficult to obtain the true measured tissue component signal, and having a great impact on the measurement result.

[0252] For the controllable measurement condition, since the mechanisms of the variation of the controllable measurement condition affecting the measurement result are different, it is difficult to suppress the influence on the measurement result by using mathematical algorithms, but the influence of the controllable measurement condition on the measurement result can be reduced to a negligible level by using an effective control method to ensure the reproducibility of the controllable measurement condition, that is, the variation of the controllable measurement condition has an impact on the measurement result comparable to the impact of random noise on the measurement result. The effective control method is not a mathematical algorithm, and it can be implemented in cooperation with hardware design. The reproducibility of the controllable measurement condition can mean that the controllable measurement condition remains within a preset variation range at each time of measuring the tissue component, so that the controllable measurement condition remains unchanged or substantially unchanged.

[0253] Based on the above, in order to improve the possibility of obtaining the true measured tissue component signal, the inventors found that for the controllable measurement condition, a reasonable processing method is to control it by using an effective control method to realize its reproducibility.

[0254] According to the embodiment of the present disclosure, the controllable measurement condition is controlled by using an effective control method, so that the influence of the change of the controllable measurement condition on the measurement result can be reduced to a negligible level, thereby avoiding the use of a complex mathematical algorithm for processing, thereby improving the possibility of obtaining a true measured tissue component signal, and further reducing the difficulty of data processing and reducing the amount of data processing.

[0255] According to the embodiment of the present disclosure, the method can further include the following operations.

[0256] The positioning feature is determined. According to the positioning feature, the measurement region is determined, wherein the measurement region is a region that satisfies the reproducibility of the controllable measurement condition. The measurement probe is arranged at a position corresponding to the measurement region.

[0257] According to the embodiment of the present disclosure, in the embodiment of the present disclosure, the measurement posture reproducibility and the measurement region reproducibility are mainly considered. The measurement posture refers to the posture of the limb supporting the measurement site. In the related art, no related content for the measurement posture is found.

[0258] Firstly, the measurement region reproducibility. The positioning deviation of the measurement region is caused by the non-uniformity of the tissue distribution and the difference in the flat state of the skin surface, and when the relative position between the measurement probe and the measurement region deviates, the transmission path of the light in the tissue will change. Therefore, in order to realize the reproducibility of the controllable measurement condition, it is necessary to ensure the measurement region reproducibility as much as possible.

[0259] Secondly, the measurement posture reproducibility. In the tissue component measurement, it is difficult for the measured object to keep the same measurement posture unchanged. Since the change of the measurement posture will cause the change of the skin state of the measurement region, and further cause the change of the transmission path of the light in the tissue, therefore, the change of the measurement posture will produce positioning error and affect the reliability of the measurement result. The skin state can include the skin surface shape and the internal structure of the skin. Therefore, it is necessary to realize the measurement posture reproducibility. The purpose of the measurement posture positioning is to make the measurement posture during the tissue component measurement be the target measurement posture, that is, if the current measurement posture is not the target measurement posture during the tissue component measurement, the current measurement posture needs to be adjusted to the target measurement posture. The target measurement posture is a measurement posture that satisfies the reproducibility of the controllable measurement condition.

[0260] However, in fact, the importance of realizing the measurement posture reproducibility is often ignored, which is reflected in the following two aspects.

[0261] Firstly, it is found that the measurement posture reproducibility is an important factor affecting the acquisition of the real measured tissue component signal. In the related art, it is generally believed that the controllable measurement condition reproducibility is caused by the measurement region reproducibility, i.e. if the measurement region reproducibility is achieved, the possibility of improving the acquisition of the real measured tissue component signal from the controllable measurement condition aspect is improved without considering other factors. In other words, in the related art, the improvement direction is around how to improve the positioning accuracy of the measurement region, and it is found that the measurement posture reproducibility is also an important factor affecting the acquisition of the real measured tissue component signal from the controllable measurement condition aspect.

[0262] Moreover, according to the above analysis, even if the measurement region reproducibility is achieved, the internal structure of the skin at the measurement region will change when the posture of the limb supporting the measurement site changes, which changes the transmission path of the light in the tissue, and thus affects the reliability of the measurement result. In other words, only ensuring the measurement region reproducibility and ignoring the measurement posture reproducibility is not conducive to improving the possibility of acquiring the real measured tissue component signal.

[0263] Secondly, the measurement posture reproducibility is not achieved in an effective way. Since the factors affecting the acquisition of the real measured tissue component signal are not studied in depth, the importance of achieving the measurement posture reproducibility is not realized, and thus in the tissue component measurement, it is believed that the measurement posture control can be achieved by the measured object itself by keeping the body stable, i.e. if the measured object believes that its body state has not changed, the measurement posture is well controlled. However, in most cases, the change of the measurement posture cannot be perceived by the measured object, and thus the error of this way of achieving the measurement posture reproducibility is large, which will greatly interfere with the measurement result. That is, even if the measurement posture is controlled in this way, since the importance of achieving the measurement posture reproducibility is not realized, this way cannot essentially guarantee the measurement posture reproducibility.

[0264] Therefore, in order to achieve the measurement region reproducibility, it is necessary to ensure the measurement posture reproducibility as much as possible, i.e. to achieve the accurate positioning of the measurement posture. Based on the above, the measurement region reproducibility needs to be based on the measurement posture reproducibility, and thus the positioning of the measurement region needs to be based on the positioning of the measurement posture.

[0265] In the positioning process, the positioning feature can be used for positioning. The positioning feature can include a posture positioning feature and a region positioning feature. The posture positioning feature is used for positioning a measurement posture, and the region positioning feature is used for positioning a measurement region. The posture positioning feature can be arranged on a measured object or a non-measured object, and the region positioning feature can be arranged on a measured object or a non-measured object. The non-measured object can include a measurement probe or other devices. The positioning feature can include a human-set positioning feature or a feature inherent to the measured object, wherein the feature inherent to the measured object can include a palm print, a fingerprint, a birthmark, a mole, or a freckle.

[0266] According to an embodiment of the present disclosure, if the human-set positioning feature is used, the human-set positioning feature will fade over time, and thus, the positioning feature needs to be set again, which can introduce new errors and affect the positioning accuracy. The feature inherent to the measured object has good stability and is not prone to setting errors.

[0267] In order to reduce the complexity of positioning and improve the positioning accuracy, the feature inherent to the measured object can be used as the positioning feature. However, even if the feature inherent to the measured object is used as the posture positioning feature, the internal structure of the skin will be affected by the change of the measurement posture, which will also cause the positioning deviation of the measurement region. Therefore, the position of the positioning feature on the measured object is not arbitrary, and needs to be determined according to the measurement site and the relationship between the measurement site and the surrounding site. For example, if the measurement site is the forearm extension side, and the surrounding site includes the wrist. For the forearm extension side, the change of the wrist state will greatly affect the skin state of the forearm extension side. Therefore, in order to improve the positioning accuracy, the positioning feature can be arranged on the forearm extension side and the back of the hand, respectively. It should be noted that if there is no feature inherent to the measured object that can be used as the positioning feature, the positioning feature can be set artificially. For example, the positioning feature can be a point-shaped marker or a graphic marker, and the graphic marker can include a cross-shaped marker.

[0268] According to an embodiment of the present disclosure, the positioning feature includes a first posture positioning feature and a region positioning feature.

[0269] According to the positioning feature, the measurement region is determined, which can include the following operations.

[0270] According to the first posture positioning feature, the current measurement posture of the measured object is adjusted to a target measurement posture. The target measurement posture is a reproducible measurement posture that meets the controllable measurement condition. In the case where the current measurement posture is the target measurement posture, the measurement region is determined according to the region positioning feature.

[0271] According to an embodiment of the present disclosure, when the measurement posture and the measurement region are positioned, the positioning of the measurement region is realized on the premise of the positioning of the measurement posture, and in the subsequent measurement process after the positioning of the measurement region is completed, the measurement region usually does not need to be positioned again, and there can be a case where the positioning of the measurement posture is needed. The condition for completing the positioning of the measurement posture is that the current measurement posture is a target measurement posture, and the target measurement posture is a reproducible measurement posture that meets the controllable measurement condition.

[0272] According to an embodiment of the present disclosure, the reason for the case where the positioning of the measurement posture can be needed is that, in the embodiment of the present disclosure, in order to bring a better use experience to the measured object, a strategy of allowing the measurement part to move within a certain range during non-measurement and positioning the measurement posture during measurement can be adopted, and during measurement, it is necessary to ensure that the current measurement posture is the target measurement posture, so that if the current measurement posture is not the target measurement posture, the adjustment of the measurement posture is needed to ensure that the current measurement posture is the target measurement posture.

[0273] Based on the above, the positioning can be divided into first measurement posture positioning, measurement region positioning, and second measurement posture positioning. The first measurement posture positioning can be understood as being performed in cooperation with the positioning of the measurement region. The second measurement posture positioning can be understood as being performed when the measurement probe is set at a position corresponding to the measurement region and the measurement posture is not the target measurement posture.

[0274] According to an embodiment of the present disclosure, the region positioning feature is used to position the measurement region. The posture positioning feature used for the first measurement posture positioning is referred to as a first posture positioning feature. The posture positioning feature used for the second measurement posture positioning is referred to as a second posture positioning feature. The region positioning feature, the first posture positioning feature, and the second posture positioning feature can be all the same, partially the same, or all different. The number of the region positioning feature, the first posture positioning feature, and the second posture positioning feature can include one or more.

[0275] When the first measurement posture positioning and the measurement region positioning are performed, the current measurement posture of the measured object can be adjusted according to the first posture positioning feature so that the first posture positioning feature matches the preset feature, and in the case where the first posture positioning feature matches the preset feature, it can be determined that the current measurement posture is the target measurement posture. In the case where the current measurement posture is the target measurement posture, the measurement region is determined according to the region positioning feature. Thus, the positioning of the measurement posture and the measurement region is completed.

[0276] It should be noted that, in terms of determining the measurement region according to the region positioning feature, it can be understood that the region corresponding to the region positioning feature is determined as the measurement region, which includes determining the region where the region positioning feature is located as the measurement region, or determining another region having an association relationship with the region positioning feature as the measurement region.

[0277] By positioning the measurement region according to the first posture positioning feature and the region positioning feature, the positioning of the measurement region and the positioning of the measurement posture are simultaneously completed.

[0278] According to an embodiment of the present disclosure, the measurement probe is arranged at a position corresponding to the measurement region, which can include the following operations.

[0279] The measurement probe is arranged at a position corresponding to the measurement region by the fixing part, wherein the fixing part is integrated with the measurement probe, partially separated or completely separated.

[0280] According to an embodiment of the present disclosure, the fixing part is used to fix the measurement probe, and the fixing part can be integrated with the measurement probe, partially separated or completely separated, that is, the fixing part can be a component of the measurement probe, can be two independent parts from the measurement probe, and can be partially a component of the measurement probe and partially an independent part from the measurement probe. The fixing part can include a fixing seat and a first matching piece, or the fixing part can include a second matching piece. The first matching piece is used to arrange the fixing seat at a position corresponding to the measurement region, and the fixing seat is used to arrange the measurement probe. The second matching piece is used to arrange the measurement probe at a position corresponding to the measurement region.

[0281] If the fixing part includes the fixing seat and the first matching piece, the fixing seat is separated from the measurement probe, and the first matching piece is integrated with or separated from the fixing seat. If the fixing part includes the second matching piece, the second matching piece is integrated with or separated from the measurement probe.

[0282] According to an embodiment of the present disclosure, the fixing part includes the fixing seat and the first matching piece. The measurement probe is arranged at a position corresponding to the measurement region by the fixing part, which can include the following operations.

[0283] The fixing seat is arranged at a position corresponding to the measurement region by the first matching piece. The measurement probe is arranged at the fixing seat.

[0284] According to an embodiment of the present disclosure, the measurement probe is not directly arranged at a position corresponding to the measurement region, but is arranged at a position corresponding to the measurement region by the fixing seat.

[0285] In the tissue component measurement process, if the measurement probe is arranged at the position corresponding to the measurement area through the fixing seat, since the fixing seat can be arranged at the measurement area for a long time without being separated from the measurement area, the measurement probe can be arranged at the fixing seat during measurement and separated from the fixing seat during non-measurement. Moreover, since the fixing seat is arranged at the position corresponding to the measurement area, when the measurement probe is separated from the fixing seat and then arranged at the fixing seat again, the positioning accuracy can still be maintained and the positioning difficulty of the measurement probe is reduced.

[0286] According to an embodiment of the present disclosure, the skin state of the skin at the measurement area satisfies a first preset condition in the process of arranging the fixing seat at the position corresponding to the measurement area through the first matching piece.

[0287] According to an embodiment of the present disclosure, the skin state of the skin at the measurement area satisfies a second preset condition in the process of arranging the measurement probe at the fixing seat.

[0288] According to an embodiment of the present disclosure, since the action of fixing the fixing seat will affect the skin state of the skin at the corresponding position and then affect the positioning accuracy of the measurement area, in order to ensure the positioning accuracy of the measurement area, the first matching piece can be caused to ensure that the skin state of the skin at the measurement area satisfies the first preset condition in the process of fixing the fixing seat. The first preset condition can refer to that the change of the skin state of the skin at the corresponding position in the process of fixing the fixing seat by the first matching piece is within a first preset range. The change of the skin state can include skin deformation. Correspondingly, the first preset range can include a first preset deformation range.

[0289] According to an embodiment of the present disclosure, since the action of fixing the measurement probe will affect the skin state of the skin at the corresponding position and then affect the positioning accuracy of the measurement area, in order to ensure the positioning accuracy of the measurement area, the fixing seat can be caused to ensure that the skin state of the skin at the measurement area satisfies the second preset condition in the process of fixing the measurement probe. The second preset condition can refer to that the change of the skin state of the skin at the corresponding position in the process of fixing the measurement probe by the fixing seat is within a second preset range. The change of the skin state can include skin deformation. Correspondingly, the second preset range can include a second preset deformation range.

[0290] According to an embodiment of the present disclosure, the measurement probe does not move in the fixing seat.

[0291] According to an embodiment of the present disclosure, when the measurement probe is fixed to the fixing seat, the problem of affecting the reproducibility of the measurement condition due to insecure fixing can also occur. In order to solve this problem, it is tried to ensure that the measurement probe does not move in the fixing seat during the tissue component measurement process.

[0292] According to an embodiment of the present disclosure, the fixing part comprises a second matching part. The operation of setting the measurement probe at the position corresponding to the measurement area through the fixing part can comprise the following operations.

[0293] The operation of setting the measurement probe at the position corresponding to the measurement area through the second matching part.

[0294] According to an embodiment of the present disclosure, the manner of setting the measurement probe at the position corresponding to the measurement area can comprise the following manners in addition to the above-mentioned manner of setting the measurement probe at the position corresponding to the measurement area through the fixing seat, i.e., the manner of directly setting the measurement probe at the position corresponding to the measurement area without the fixing seat, which needs the second matching part to cooperate.

[0295] It should be noted that the above-mentioned manner of not needing the fixing seat can comprise the following two understandings, one of which is that the measurement probe is provided with a structure on the measurement probe which plays the same role as the independent fixing seat. The second understanding is that the measurement probe is not provided with a structure which plays the same role as the independent fixing seat.

[0296] According to an embodiment of the present disclosure, the skin state of the skin at the measurement area meets a third preset condition in the process of setting the measurement probe at the position corresponding to the measurement area through the second matching part.

[0297] According to an embodiment of the present disclosure, since the action of fixing the measurement probe will affect the skin state of the skin at the corresponding position, and further affect the positioning accuracy of the measurement area, in order to ensure the positioning accuracy of the measurement area, the second matching part can be used to ensure that the skin state of the skin at the measurement area meets the third preset condition in the process of fixing the measurement probe. The third preset condition can refer to that the change of the skin state of the skin at the corresponding position in the process of fixing the measurement probe by the second matching part is within a third preset range. The change of the skin state can comprise skin deformation. Correspondingly, the third preset range can comprise a third preset deformation range.

[0298] According to an embodiment of the present disclosure, the operation of determining the measurement area according to the area positioning feature can comprise the following operations.

[0299] The first projection feature is acquired. In a case where it is determined that the area positioning feature does not match the first projection feature, the position of the measurement probe and / or the fixing part is adjusted until the area positioning feature matches the first projection feature. In a case where it is determined that the area positioning feature matches the first projection feature, the area corresponding to the measurement probe and / or the fixing part is determined as the measurement area.

[0300] According to an embodiment of the present disclosure, in order to guarantee flexibility of use and accuracy of measurement region positioning, an optical method can be adopted, i.e., matching the region positioning feature with the first projection feature, and determining the measurement region according to the matching result, wherein the first projection feature is formed according to the optical method, i.e., projecting a light spot of a preset shape by a light source, and the shape of the light spot can be determined according to the region positioning feature. For example, the light spot of the preset shape is a cross-shaped light spot.

[0301] After the first projection feature is obtained, it is determined whether the region positioning feature matches the first projection feature, and in a case where it is determined that the region positioning feature does not match the first projection feature, the position of the measurement probe and the fixing part can be adjusted so that the region positioning feature matches the first projection feature until the region positioning feature matches the first projection feature. In a case where it is determined that the region positioning feature matches the first projection feature, it can be indicated that the region where the measurement probe and the fixing part are currently located is the measurement region.

[0302] After the first projection feature is obtained by using the structure for projecting the first projection feature, it is determined whether the region positioning feature matches the first projection feature, and in a case where it is determined that the region positioning feature does not match the first projection feature, the position of the measurement probe and / or the fixing seat can be adjusted so that the region positioning feature matches the first projection feature until the region positioning feature matches the first projection feature. In a case where it is determined that the region positioning feature matches the first projection feature, it can be indicated that the region where the measurement probe and / or the fixing seat are currently located is the measurement region.

[0303] According to an embodiment of the present disclosure, the structure for projecting the first projection feature can be arranged on the measured object, the measurement probe, the fixing seat or other objects. The other objects can represent objects other than the measurement probe, the fixing part and the measured object. The region positioning feature can be arranged on at least one of the measurement probe, the fixing seat, the measured object and the other objects. The adjustment process based on the optical method is described below from two angles of the arrangement position of the structure for projecting the first projection feature and the arrangement position of the region positioning feature.

[0304] The adjustment process based on the optical method is described below from the angle of the arrangement position of the structure for projecting the first projection feature.

[0305] First, if the structure for projecting the first projection feature is arranged on the measured object, the area positioning feature can be arranged on at least one of the measured object, the measurement probe, the fixing base and other objects. It should be noted that if the area positioning feature is arranged on the measured object or other objects, the positioning of the measurement area can be achieved by adjusting the position of the measurement probe and / or the fixing base according to the area positioning feature and the first projection feature until the area positioning feature matches the first projection feature, where the area positioning feature matches the first projection feature means that the area positioning feature is blocked by the measurement probe and / or the fixing base, so that the first projection feature cannot be projected to the position where the area positioning feature is located. If the area positioning feature does not match the first projection feature, at least one first projection feature can be projected to the position where the area positioning feature is located.

[0306] Second, if the structure for projecting the first projection feature is arranged on the measurement probe, the area positioning feature cannot be arranged on the measurement probe, and can be arranged on the measured object, the fixing base or other objects. It should be noted that if the area positioning feature is arranged on the fixing base, and the positioning of the measurement probe is achieved by arranging the measurement probe at a position corresponding to the measurement area by the fixing part provided with the fixing base, in order to achieve the positioning of the measurement area, the following method can be used, i.e. adjusting the position of the fixing base. Before the area positioning feature matches the first projection feature, the position of the measurement probe is fixed, and the position of the fixing base is adjusted according to the area positioning feature and the first projection feature until the area positioning feature matches the first projection feature, and in the case where the two match, the area corresponding to the fixing base is determined as the measurement area, so that the measurement probe can be arranged on the fixing base.

[0307] Third, if the structure for projecting the first projection feature is arranged on the fixing base, the area positioning feature cannot be arranged on the fixing base, and can be arranged on the measured object, the measurement probe or other objects. It should be noted that if the area positioning feature is arranged on the measurement probe, and the positioning of the measurement probe is achieved by arranging the measurement probe at a position corresponding to the measurement area by the fixing part provided with the fixing base, in order to achieve the positioning of the measurement area, the following method can be used, i.e. adjusting the position of the fixing base. Before the area positioning feature matches the first projection feature, the position of the measurement probe is fixed, and the position of the fixing base is adjusted according to the area positioning feature and the first projection feature until the area positioning feature matches the first projection feature, and in the case where the two match, the area corresponding to the fixing base is determined as the measurement area, so that the measurement probe can be arranged on the fixing base.

[0308] Fourthly, if the structure for projecting the first projection feature is arranged on the other object, the region positioning feature can be arranged on at least one of the measured object, the measurement probe, the fixing base and the other object. It should be noted that if the region positioning feature is arranged on the measured object or the other object, the positioning of the measurement region can be realized in a similar way as that the structure for projecting the first projection feature is arranged on the measured object and the region positioning feature is arranged on the measured object or the other object, which will not be repeated here.

[0309] The above is explained from the perspective of the arrangement position of the region positioning feature.

[0310] Firstly, if the region positioning feature is arranged on the measured object, the structure for projecting the first projection feature can be arranged on the measured object, the measurement probe, the fixing base or the other object. It should be noted that if the structure for projecting the first projection feature is arranged on the measured object or the other object, the positioning of the measurement region can be realized by adjusting the position of the measurement probe and / or the fixing base according to the region positioning feature and the first projection feature until the region positioning feature and the first projection feature match, wherein the region positioning feature and the first projection feature match means that the region positioning feature is shielded by the measurement probe and / or the fixing base so that the first projection feature cannot be projected to the position where the region positioning feature is located. If the region positioning feature and the first projection feature do not match, at least one first projection feature can be projected to the position where the region positioning feature is located.

[0311] Secondly, if the region positioning feature is arranged on the measurement probe, the structure for projecting the first projection feature is separate from the measurement probe and can be arranged on the measured object, the fixing base or the other object. It should be noted that if the structure for projecting the first projection feature is arranged on the fixing base, the corresponding part of the above description can be referred to, which will not be repeated here.

[0312] Thirdly, if the region positioning feature is arranged on the fixing base, the structure for projecting the first projection feature is separate from the fixing base and can be arranged on the measured object, the measurement probe or the other object. It should be noted that if the structure for projecting the first projection feature is arranged on the measurement probe, the corresponding part of the above description can be referred to, which will not be repeated here.

[0313] Fourthly, if the region positioning feature is arranged on the other object, the structure for projecting the first projection feature can be arranged on the measured object, the measurement probe, the fixing base or the other object. It should be noted that if the structure for projecting the first projection feature is arranged on the measured object or the other object, the corresponding part of the above description can be referred to, which will not be repeated here.

[0314] Exemplarily, Figure 7A schematic diagram of positioning a measurement region based on an optical method is shown. Figure 7 The region positioning feature is arranged on the measurement probe. Figure 8 A schematic diagram of positioning a measurement region based on an optical method is shown. Figure 8 The region positioning feature is arranged on the measured object.

[0315] The positioning of the measurement region is achieved by the optical method. On the one hand, the position and angle of the light source can be flexibly adjusted, so that it can be more easily matched with the region positioning feature. Therefore, the region positioning feature can be flexibly arranged, thereby reducing the difficulty of arranging the region positioning feature. On the other hand, the shape of the Raman scattering spot can be adjusted to better match the region positioning feature and improve the positioning accuracy.

[0316] According to an embodiment of the present disclosure, determining the measurement region according to the region positioning feature can include the following operations.

[0317] A first target image is acquired. A first template image is acquired, wherein the first template image includes the region positioning feature. In a case where it is determined that the first target image does not match the first template image, the position of the measurement probe and / or the fixing part is adjusted to acquire a new first target image until the new first target image matches the first template image. In a case where it is determined that the first target image matches the first template image, the region corresponding to the measurement probe and / or the fixing part is determined as the measurement region.

[0318] According to an embodiment of the present disclosure, in order to ensure flexibility and accuracy of the positioning of the measurement region, an image matching method can be used, that is, the first target image is matched with the first template image, and the measurement region is determined according to the matching result. The first template image can include the region positioning feature, and the position of the region positioning feature in the first template image is a preset position. In the process of matching the first target image with the first template image, the first target image can be a target image that does not include the region positioning feature, or a target image that includes the region positioning feature but the position of the region positioning feature in the first target image is not the preset position, or a target image that includes the region positioning feature and the position of the region positioning feature in the first target image is the preset position. Since the first template image includes the region positioning feature at the preset position, if the first target image matches the first template image, it can be concluded that the first target image includes the region positioning feature and the position of the region positioning feature in the first target image is the preset position. In other words, the purpose of matching the first target image with the first template image is to make the acquired first target image include the region positioning feature and the position of the region positioning feature in the first target image be the preset position.

[0319] According to an embodiment of the present disclosure, in a case where it is determined that the first target image matches the first template image, it can be indicated that the region where the measurement probe and the fixing part are currently located is the measurement region. The determination of whether the first target image matches the first template image can include determination of a similarity of the first target image and the first template image. In a case where the similarity is greater than or equal to a similarity threshold, it is determined that the first target image matches the first template image. In a case where the similarity is less than the similarity threshold, it is determined that the first target image does not match the first template image. The determination of the similarity of the first target image and the first template image can include correlation analysis of the first target image and the first template image to obtain a correlation coefficient, and determination of the similarity of the first target image and the first template image according to the correlation coefficient.

[0320] According to an embodiment of the present disclosure, the structure for collecting the first target image can be arranged on the measured object, the measurement probe, the fixing seat or other objects. The other objects can represent objects other than the measurement probe, the fixing part and the measured object. The region positioning feature can be arranged on at least one of the measurement probe, the fixing seat, the measured object and the other objects. For the description of the structure for collecting the first target image and the region positioning feature, reference can be made to the description of the structure for projecting the first projection feature and the region positioning feature, which will not be repeated here. The difference is that if the structure for collecting the first target image is arranged on the measurement probe, the region positioning feature can be arranged on at least one of the measured object, the measurement probe, the fixing seat and the other objects. If the structure for collecting the first target image is arranged on the fixing seat, the region positioning feature can be arranged on at least one of the measured object, the measurement probe, the fixing seat and the other objects.

[0321] Exemplarily, Figure 9 A schematic diagram of positioning of a measurement region according to an embodiment of the present disclosure is schematically shown. Figure 9 In the embodiment, the region positioning feature is arranged on the measurement probe. Figure 10 A schematic diagram of positioning of a measurement region according to another embodiment of the present disclosure is schematically shown. Figure 10 In the embodiment, the region positioning feature is arranged on the measured object.

[0322] According to an embodiment of the present disclosure, the determination of the measurement region according to the region positioning feature can include the following operations.

[0323] acquire a second target image, wherein the second target image comprises the region positioning feature. In a case where a position of the region positioning feature in the second target image is not the first preset position, adjust a position of the measurement probe and / or the fixing part to acquire a new second target image until the position of the region positioning feature in the new second target image is the first preset position. In a case where the position of the region positioning feature in the new second target image is the first preset position, determine a region corresponding to the measurement probe and / or the fixing part as the measurement region.

[0324] According to an embodiment of the present disclosure, in order to guarantee flexibility of use and accuracy of measurement region positioning, an imaging method can be adopted, that is, if the position of the region positioning feature in the second target image is the first preset position, it can be indicated that positioning of the measurement region is completed.

[0325] According to an embodiment of the present disclosure, the process of positioning the measurement region by adopting the imaging method is a process of determining whether the position of the region positioning feature in the second target image is the first preset position. If the position of the region positioning feature in the second target image is not the first preset position, the position of the measurement probe and the fixing part can be adjusted to acquire a new second target image until the position of the region positioning feature in the new second target image is the first preset position. In a case where the position of the region positioning feature in the new second target image is the first preset position, it can be indicated that a region where the measurement probe and the fixing part are currently located is the measurement region.

[0326] According to an embodiment of the present disclosure, the structure for acquiring the second target image can be arranged on the measured object, the measurement probe, the fixing seat or other objects. The other objects can represent objects other than the measurement probe, the fixing part and the measured object. The region positioning feature can be arranged on at least one of the measurement probe, the fixing seat, the measured object and the other objects. For the structure for acquiring the second target image and the region positioning feature, refer to the description of the structure for projecting the first projection feature and the region positioning feature, which will not be described herein again.

[0327] An exemplary imaging method for positioning a measurement region is shown in FIG. 2. Figure 11 An exemplary imaging method for positioning a measurement region is shown in FIG. 2. Figure 11 In the embodiment shown in FIG. 2, the region positioning feature is arranged on the measurement probe. Figure 11 An exemplary imaging method for positioning a measurement region is shown in FIG. 2. Figure 12 In the embodiment shown in FIG. 2, the region positioning feature is arranged on the measured object. Figure 12 In the embodiment shown in FIG. 2, movement of the measurement probe and the fixing seat changes the relative position of the two and the position of the region positioning feature presented in the image is located at the first preset position.

[0328] According to an embodiment of the present disclosure, adjusting the current measurement posture of the measured object to the target measurement posture according to the first posture positioning feature can include the following operations.

[0329] The second projection feature is acquired. In a case where it is determined that the first posture positioning feature does not match the second projection feature, the current measurement posture is adjusted until the first posture positioning feature matches the second projection feature. In a case where it is determined that the first posture positioning feature matches the second projection feature, the current measurement posture is determined as the target measurement posture.

[0330] According to an embodiment of the present disclosure, in order to ensure flexibility of use and accuracy of measurement posture positioning, an optical method can be used to achieve the matching of the first posture positioning feature and the second projection feature, and the target measurement posture is determined according to the matching result. The second projection feature is formed according to the optical method, that is, the second projection feature is formed by a light spot of a preset shape projected by a light source, and the shape of the light spot can be determined according to the first posture positioning feature. That is, for the measured object, the second projection feature matching the first posture positioning feature is set according to the first posture positioning feature, so that the current measurement posture in which the first posture positioning feature matches the second projection feature is the target measurement posture.

[0331] According to an embodiment of the present disclosure, the structure for projecting the second projection feature can be arranged on the measured object, the measurement probe, the fixing seat or other objects. The other objects can represent objects other than the measurement probe, the fixing seat and the measured object. The first posture positioning feature can be arranged on at least one of the measurement probe, the fixing seat, the measured object and the other objects. The adjustment process based on the optical method is described below from two angles of the arrangement position of the structure for projecting the second projection feature and the arrangement position of the first posture positioning feature.

[0332] The adjustment process based on the optical method is described below from the angle of the arrangement position of the structure for projecting the second projection feature.

[0333] First, if the structure for projecting the second projection feature is arranged on the measured object, the first posture positioning feature can be arranged on at least one of the measured object, the measurement probe, the fixing seat and the other objects. It should be noted that if the first posture positioning feature is arranged on the measurement probe, in order to achieve the positioning of the measurement posture, the position of the measurement probe needs to be fixed during the first measurement posture positioning stage. Similarly, if the first posture positioning feature is arranged on the fixing seat, in order to achieve the positioning of the measurement posture, the position of the fixing seat needs to be fixed during the first measurement posture positioning stage.

[0334] Secondly, if the structure for projecting the second projection feature is arranged on the measurement probe, the first posture positioning feature cannot be arranged on the measurement probe, and can be arranged on the measured object, the fixed seat or other objects. It should be noted that the position of the measurement probe needs to be fixed during the first measurement posture positioning stage. In addition, if the first posture positioning feature is arranged on the fixed seat, the positioning of the first measurement posture can be achieved by adjusting the current measurement posture of the measured object according to the first posture positioning feature and the second projection feature until the first posture positioning feature and the second projection feature match, that is, the first posture positioning feature is blocked by the measured object, so that the second projection feature cannot be projected to the position of the first posture positioning feature. If the first posture positioning feature and the second posture positioning feature do not match, at least one second projection feature can be projected to the position of the first posture positioning feature. If the first posture positioning feature is arranged on other objects, the positioning of the measurement posture can be achieved in a similar manner to arranging the first posture positioning feature on the fixed seat, which will not be described here.

[0335] Thirdly, if the structure for projecting the second projection feature is arranged on the fixed seat, the first posture positioning feature cannot be arranged on the fixed seat, and can be arranged on the measured object, the measurement probe or other objects. It should be noted that the position of the fixed seat needs to be fixed during the first measurement posture positioning stage. In addition, if the first posture positioning feature is arranged on the measurement probe or other objects, the positioning of the measurement posture can be achieved in a similar manner to arranging the structure for projecting the second projection feature on the measurement probe and arranging the first posture positioning feature on the fixed seat or other objects, which will not be described here.

[0336] Fourthly, if the structure for projecting the second projection feature is arranged on other objects, the first posture positioning feature can be arranged on at least one of the measured object, the measurement probe, the fixed seat and other objects. It should be noted that if the first posture positioning feature is arranged on the measurement probe, the fixed seat or other objects, the positioning of the measurement posture can be achieved in a similar manner to arranging the structure for projecting the second projection feature on the measurement probe and arranging the first posture positioning feature on the fixed seat or other objects, which will not be described here.

[0337] The setting position of the first posture positioning feature will be described from the perspective of the setting position of the first posture positioning feature.

[0338] First, if the first posture positioning feature is arranged on the measured object, the structure for projecting the second projection feature can be arranged on the measured object, the measurement probe, the fixed seat or other objects. It should be noted that if the structure for projecting the second projection feature is arranged on the measurement probe, the position of the measurement probe needs to be fixed during the first measurement posture positioning phase. Similarly, if the structure for projecting the second projection feature is arranged on the fixed seat, the position of the fixed seat needs to be fixed during the first measurement posture positioning phase.

[0339] Second, if the first posture positioning feature is arranged on the measurement probe, the structure for projecting the second projection feature is separate from the measurement probe and can be arranged on the measured object, the fixed seat or other objects. It should be noted that if the structure for projecting the second projection feature is arranged on the measured object, the fixed seat or other objects, refer to the corresponding part of the above description, which will not be repeated here.

[0340] Third, if the first posture positioning feature is arranged on the fixed seat, the structure for projecting the second projection feature is separate from the fixed seat and can be arranged on the measured object, the measurement probe or other objects. It should be noted that if the structure for projecting the second projection feature is arranged on the measured object, the measurement probe or other objects, refer to the corresponding part of the above description, which will not be repeated here.

[0341] Fourth, if the first posture positioning feature is arranged on other objects, the structure for projecting the second projection feature can be arranged on the measured object, the measurement probe, the fixed seat or other objects. It should be noted that if the structure for projecting the second projection feature is arranged on the measured object, the measurement probe, the fixed seat or other objects, refer to the corresponding part of the above description, which will not be repeated here.

[0342] Exemplarily, Figure 13 A schematic diagram of implementing positioning of a measurement posture based on an optical method according to an embodiment of the present disclosure is schematically shown. Figure 13 The first posture positioning feature is arranged on the measured object.

[0343] The positioning of the measurement posture is implemented by the optical method. On the one hand, the position and angle of the light source can be flexibly adjusted, so that it can be more easily matched with the first posture positioning feature. Therefore, the first posture positioning feature can be flexibly arranged, thereby reducing the difficulty of arranging the first posture positioning feature. On the other hand, the shape of the Raman scattering spot can be adjusted to better match the first posture positioning feature and improve the positioning accuracy.

[0344] According to an embodiment of the present disclosure, adjusting the current measurement posture of the measured object to the target measurement posture according to the first posture positioning feature can include the following operations.

[0345] The third target image is acquired. The second template image is acquired, where the second template image includes the first posture positioning feature. In a case where it is determined that the third target image does not match the second template image, the current measurement posture is adjusted to acquire a new third target image until the new third target image matches the second template image. In a case where it is determined that the new third target image matches the second template image, the current measurement posture is determined as the target measurement posture.

[0346] According to an embodiment of the present disclosure, in order to guarantee flexibility of use and accuracy of measurement posture positioning, an image matching method can be adopted, that is, the third target image is matched with the second template image, and the target measurement posture is determined according to a matching result. The second template image can include the first posture positioning feature and a position of the first posture positioning feature in the second template image is a preset position. In the process of matching the third target image with the second template image, the third target image can be a target image that does not include the first posture positioning feature, can be a target image that includes the first posture positioning feature but a position of the first posture positioning feature in the third target image is not the preset position, or can be a target image that includes the first posture positioning feature and a position of the first posture positioning feature in the third target image is the preset position. Since the second template image includes the first posture positioning feature at the preset position, if the third target image matches the second template image, it can be indicated that the third target image includes the first posture positioning feature and a position of the first posture positioning feature in the third target image is the preset position. In other words, the purpose of matching the third target image with the second template image is to make the acquired third target image include the first posture positioning feature and a position of the first posture positioning feature in the third target image is the preset position.

[0347] According to an embodiment of the present disclosure, in a case where it is determined that the third target image matches the second template image, it can be indicated that the current measurement posture is the target measurement posture.

[0348] According to an embodiment of the present disclosure, the structure for capturing the third target image can be arranged on the measured object, the measurement probe, the fixing base or other objects. The other objects can represent objects other than the measurement probe, the fixing base and the measured object. The first posture positioning feature can be arranged on at least one of the measurement probe, the fixing base, the measured object and the other objects. For the description of the structure for capturing the third target image and the first posture positioning feature, reference can be made to the description of the structure for projecting the second projection feature and the first posture positioning feature, which will not be repeated here. The difference is that if the structure for capturing the third target image is arranged on the measurement probe, the first posture positioning feature can be arranged on at least one of the measured object, the measurement probe, the fixing base and the other objects. If the structure for capturing the third target image is arranged on the fixing base, the first posture positioning feature can be arranged on at least one of the measured object, the measurement probe, the fixing base and the other objects.

[0349] Exemplarily, Figure 14 A schematic diagram of a method for image matching to realize positioning of a measurement posture according to an embodiment of the present disclosure is shown schematically. Figure 14 In the first posture positioning feature is arranged on the measured object.

[0350] According to an embodiment of the present disclosure, adjusting the current measurement posture of the measured object to the target measurement posture according to the first posture positioning feature can include the following operations.

[0351] A fourth target image is acquired, wherein the fourth target image includes the first posture positioning feature. In a case where the position of the first posture positioning feature in the fourth target image is not at the second preset position, the current measurement posture is adjusted to acquire a new fourth target image until the position of the first posture positioning feature in the new fourth target image is at the second preset position. In a case where the position of the first posture positioning feature in the new fourth target image is at the second preset position, the current measurement posture is determined as the target measurement posture.

[0352] According to an embodiment of the present disclosure, in order to ensure flexibility of use and accuracy of positioning of the measurement posture, an imaging method can be used, i.e. if the position of the first posture positioning feature in the fourth target image is at the second preset position, it can be indicated that the positioning of the measurement posture is completed.

[0353] According to an embodiment of the present disclosure, the process of measuring the position of the posture by using the imaging method is a process of determining whether the position of the first posture positioning feature in the fourth target image is the second preset position. If the position of the first posture positioning feature in the fourth target image is not the second preset position, the current measurement posture can be adjusted to obtain a new fourth target image, until the position of the first posture positioning feature in the new fourth target image is the second preset position. In the case that the position of the first posture positioning feature in the new fourth target image is the second preset position, it can be indicated that the current measurement posture is the target measurement posture.

[0354] According to an embodiment of the present disclosure, the structure for collecting the fourth target image can be arranged on the measured object, the measurement probe, the fixed seat or other objects. The other objects can represent objects other than the measurement probe, the fixed seat and the measured object. The first posture positioning feature can be arranged on at least one of the measurement probe, the fixed seat, the measured object and the other objects. For the description of the structure for collecting the fourth target image and the first posture positioning feature, please refer to the description of the structure for projecting the second projection feature and the first posture positioning feature, which will not be repeated here.

[0355] Exemplarily, Figure 15 An exemplary diagram for measuring the position of the posture by using the imaging method according to an embodiment of the present disclosure is shown schematically. Figure 15 In the embodiment, the first posture positioning feature is arranged on the measured object.

[0356] According to an embodiment of the present disclosure, the method can further include the following operations.

[0357] If the measurement probe is arranged at a position corresponding to the measurement region, in the case that the current measurement posture is determined to be not the target measurement posture, the second posture positioning feature is determined. According to the second posture positioning feature, the current measurement posture is adjusted to the target measurement posture.

[0358] According to an embodiment of the present disclosure, in the case that the current measurement posture is determined to be not the target measurement posture, the above-mentioned re-measuring the position of the posture needs to be performed. The current measurement posture can be adjusted according to the second posture positioning feature, until the current measurement posture is the target measurement posture. The second posture positioning feature can be the same as or different from the first posture positioning feature.

[0359] According to an embodiment of the present disclosure, adjusting the current measurement posture to the target measurement posture according to the second posture positioning feature can include the following operations.

[0360] The third projection feature is acquired. In a case where it is determined that the second posture positioning feature does not match the third projection feature, the current measurement posture is adjusted until the second posture positioning feature matches the third projection feature. In a case where it is determined that the second posture positioning feature matches the third projection feature, the current measurement posture is determined as the target measurement posture.

[0361] According to an embodiment of the present disclosure, in order to guarantee flexibility of use and accuracy of measurement posture positioning, an optical method can be adopted, i.e., the second posture positioning feature is matched with the third projection feature, and according to a matching result, the target measurement posture is determined, wherein the third projection feature is formed according to the optical method, i.e., the third projection feature is formed by a light spot of a preset shape projected by a light source, and the shape of the light spot can be determined according to the second posture positioning feature. That is, for the measured object, the third projection feature matched with the second posture positioning feature is set, so that the current measurement posture in which the second posture positioning feature matches the third projection feature is the target measurement posture.

[0362] According to an embodiment of the present disclosure, the structure for projecting the third projection feature can be arranged on the measured object, the measurement probe, the fixed seat or other objects. The other objects can represent objects other than the measurement probe, the fixed seat and the measured object. The second posture positioning feature can be arranged on at least one of the measurement probe, the fixed seat, the measured object and the other objects. The adjustment process based on the optical method is described below from two angles of the arrangement position of the structure for projecting the third projection feature and the arrangement position of the second posture positioning feature.

[0363] The adjustment process based on the optical method is described below from the angle of the arrangement position of the structure for projecting the third projection feature.

[0364] Firstly, if the structure for projecting the third projection feature is arranged on the measured object, the second posture positioning feature can be arranged on at least one of the measured object, the measurement probe, the fixed seat and the other objects.

[0365] Secondly, if the structure for projecting the third projection feature is arranged on the measurement probe, the second posture positioning feature cannot be arranged on the measurement probe and the fixed seat, and can be arranged on the measured object or the other objects, which is caused by the arrangement of the measurement probe on the fixed seat after the measurement probe is arranged on the position corresponding to the measurement region.

[0366] Thirdly, if the structure for projecting the third projection feature is arranged on the fixed seat, the second posture positioning feature cannot be arranged on the measurement probe and the fixed seat, and can be arranged on the measured object or the other objects, which is also caused by the arrangement of the measurement probe on the fixed seat after the measurement probe is arranged on the position corresponding to the measurement region.

[0367] Fourthly, if the second pose positioning feature is arranged on the measured object, the structure for projecting the third projection feature can be arranged on the measured object, the measurement probe, the fixing base or other objects.

[0368] The second pose positioning feature is explained from the perspective of the arrangement position.

[0369] Firstly, if the second pose positioning feature is arranged on the measured object, the structure for projecting the third projection feature can be arranged on the measured object, the measurement probe, the fixing base or other objects.

[0370] Secondly, if the second pose positioning feature is arranged on the measurement probe, the structure for projecting the third projection feature is separate from the measurement probe and the fixing base, and can be arranged on the measured object or other objects, which is caused by the arrangement of the measurement probe on the position corresponding to the measurement area after the arrangement of the measurement probe on the fixing base.

[0371] Thirdly, if the second pose positioning feature is arranged on the fixing base, the structure for projecting the third projection feature is separate from the measurement probe and the fixing base, and can be arranged on the measured object or other objects, which is caused by the arrangement of the measurement probe on the position corresponding to the measurement area after the arrangement of the measurement probe on the fixing base.

[0372] Fourthly, if the second pose positioning feature is arranged on other objects, the structure for projecting the third projection feature can be arranged on the measured object, the measurement probe, the fixing base or other objects. It should be noted that if the structure for projecting the third projection feature is arranged on other objects, refer to the corresponding part of the above description, which will not be repeated here.

[0373] The optical method is used to realize the positioning of the measurement posture. On one hand, the position and angle of the light source can be flexibly adjusted, so that the second posture positioning feature can be matched more easily. Therefore, the second posture positioning feature can be flexibly set, thereby reducing the difficulty of setting the second posture positioning feature. On the other hand, the shape of the Raman scattering spot can be adjusted to better match the second posture positioning feature, thereby improving the positioning accuracy.

[0374] According to an embodiment of the present disclosure, adjusting the current measurement posture to the target measurement posture according to the second posture positioning feature can include the following operations.

[0375] The fifth target image is acquired. The third template image is acquired, where the third template image includes the second posture positioning feature. In a case where it is determined that the fifth target image does not match the third template image, the current measurement posture is adjusted to acquire a new fifth target image until the new fifth target image matches the third template image. In a case where it is determined that the new fifth target image matches the third template image, it is determined that the current measurement posture is the target measurement posture.

[0376] According to an embodiment of the present disclosure, in order to ensure flexibility and accuracy of the measurement posture positioning, an image matching method can be used, that is, the fifth target image is matched with the third template image, and the target measurement posture is determined according to the matching result. The third template image can include the second posture positioning feature, and the position of the second posture positioning feature in the third template image is a preset position. In the process of matching the fifth target image with the third template image, the fifth target image can be a target image that does not include the second posture positioning feature, can be a target image that includes the second posture positioning feature but the position of the second posture positioning feature in the fifth target image is not the preset position, or can be a target image that includes the second posture positioning feature and the position of the second posture positioning feature in the fifth target image is the preset position. Since the third template image includes the second posture positioning feature at the preset position, if the fifth target image matches the third template image, it can be indicated that the fifth target image includes the second posture positioning feature and the position of the second posture positioning feature in the fifth target image is the preset position. In other words, the purpose of matching the fifth target image with the third template image is to make the acquired fifth target image include the second posture positioning feature and the position of the second posture positioning feature in the fifth target image is the preset position.

[0377] According to an embodiment of the present disclosure, in a case where it is determined that the fifth target image matches the third template image, it can be indicated that the current measurement posture is the target measurement posture.

[0378] According to an embodiment of the present disclosure, the structure for capturing the fifth target image can be arranged on the measured object, the measurement probe, the fixing base or other objects. The other objects can represent objects other than the measurement probe, the fixing base and the measured object. The second pose positioning feature can be arranged on at least one of the measurement probe, the fixing base, the measured object and the other objects. For the description of the structure for capturing the fifth target image and the second pose positioning feature, reference can be made to the description of the structure for projecting the third projection feature and the second pose positioning feature, which will not be repeated here. The difference is that if the structure for capturing the fifth target image is arranged on the measurement probe, the second pose positioning feature can be arranged on at least one of the measured object, the measurement probe, the fixing base and the other objects. If the structure for capturing the fifth target image is arranged on the fixing base, the second pose positioning feature can be arranged on at least one of the measured object, the measurement probe, the fixing base and the other objects.

[0379] According to an embodiment of the present disclosure, adjusting the current measurement pose to the target measurement pose according to the second pose positioning feature can include the following operations.

[0380] capturing a sixth target image, wherein the sixth target image includes the second pose positioning feature. In a case where the position of the second pose positioning feature in the sixth target image is not at the third preset position, adjusting the current measurement pose to capture a new sixth target image until the position of the second pose positioning feature in the new sixth target image is at the third preset position. In a case where the position of the second pose positioning feature in the new sixth target image is at the third preset position, determining that the current measurement pose is the target measurement pose.

[0381] According to an embodiment of the present disclosure, in order to ensure flexibility of use and accuracy of measurement pose positioning, an imaging method can be used to achieve that, i.e. if the position of the second pose positioning feature in the sixth target image is the third preset position, it can be indicated that the positioning of the measurement pose is completed.

[0382] According to an embodiment of the present disclosure, the process of using the imaging method to achieve the measurement pose positioning is the process of determining whether the position of the second pose positioning feature in the sixth target image is the third preset position. If the position of the second pose positioning feature in the sixth target image is not the third preset position, the current measurement pose can be adjusted to capture a new sixth target image until the position of the second pose positioning feature in the new sixth target image is the third preset position. In a case where the position of the second pose positioning feature in the new sixth target image is the third preset position, it can be indicated that the current measurement pose is the target measurement pose.

[0383] According to an embodiment of the present disclosure, the structure for capturing the sixth target image can be arranged on the measured object, the measurement probe, the fixing seat or other objects. The other objects can represent objects other than the measurement probe, the fixing seat and the measured object. The second pose positioning feature can be arranged on at least one of the measurement probe, the fixing seat, the measured object and the other objects. For the structure for capturing the sixth target image and the second pose positioning feature, refer to the description of the structure for projecting the third projection feature and the second pose positioning feature, which will not be repeated here.

[0384] According to an embodiment of the present disclosure, the method can further include the following operations.

[0385] Generating prompt information, wherein the prompt information is used to prompt that the measurement pose positioning and / or the measurement region positioning are completed, and the form of the prompt information includes at least one of an image, a voice or a vibration.

[0386] According to an embodiment of the present disclosure, in order to enable the user to know whether the measurement pose positioning and / or the measurement region positioning are completed in time, prompt information can be generated after the measurement pose positioning and / or the measurement region positioning are completed. The specific form of the prompt information can include at least one of an image, a voice and a vibration.

[0387] According to an embodiment of the present disclosure, the method can further include the following operations.

[0388] In a case where it is determined that the fixing seat is arranged at a position corresponding to the measurement region and the measurement probe is not arranged on the fixing seat, the measurement probe is arranged on the fixing seat. In a case where it is determined that the fixing seat is not arranged at a position corresponding to the measurement region, the fixing seat is arranged at a position corresponding to the measurement region by the first matching member, and the measurement probe is arranged on the fixing seat.

[0389] According to an embodiment of the present disclosure, if the measurement probe is arranged at a position corresponding to the measurement region by the fixing seat, the fixing seat can be separated from the measurement region and the measurement probe can be separated from the fixing seat during the tissue composition measurement process. If the fixing seat is not arranged at a position corresponding to the measurement region when measurement is needed, the fixing seat can be arranged at a position corresponding to the measurement region by the first matching member, and the measurement probe can be arranged on the fixing seat. If the fixing seat is arranged at a position corresponding to the measurement region and the measurement probe is not arranged on the fixing seat, the measurement probe can be arranged on the fixing seat.

[0390] For example, for short-term measurement, the fixed seat can be arranged at a position corresponding to the measurement area, the measurement probe can be separated from the fixed seat, and the measurement probe can be arranged in the fixed seat when measurement is needed. For long-term measurement, the fixed seat can be separated from the measurement area, the measurement probe can be separated from the fixed seat, and the fixed seat can be arranged at a position corresponding to the measurement area by the first matching part and the measurement probe can be arranged in the fixed seat when measurement is needed.

[0391] According to an embodiment of the present disclosure, the method can further include the following operations.

[0392] In a case where it is determined that the measurement probe is not arranged at a position corresponding to the measurement area, the measurement probe is arranged at a position corresponding to the measurement area by the second matching part.

[0393] According to an embodiment of the present disclosure, if the measurement probe is directly arranged at a position corresponding to the measurement area, the measurement probe can be separated from the measurement area during the tissue component measurement, and the measurement probe can be arranged at a position corresponding to the measurement area by the second matching part when measurement is needed.

[0394] According to an embodiment of the present disclosure, the photosensitive surface is obtained after a mask plate is arranged on the initial photosensitive surface, and the light transmittance of the mask plate is less than or equal to a light transmittance threshold.

[0395] According to an embodiment of the present disclosure, the shape of the mask plate is determined according to the jitter distribution of the Raman scattered light.

[0396] According to an embodiment of the present disclosure, since the circular photosensitive surface or the square photosensitive surface is relatively common at present, the manufacturing process is less difficult and the manufacturing cost is lower, and other shapes of the photosensitive surface usually need to be customized, the manufacturing process is more difficult and the manufacturing cost is higher, therefore, if limited by the manufacturing cost, the mask plate can be arranged on the initial photosensitive surface, and the part of the initial photosensitive surface blocked by the mask plate is difficult to receive the light intensity value because the light transmittance of the mask plate is less than or equal to the light transmittance threshold.

[0397] Based on the above, the shape and position of the mask plate can be set according to the actual required shape and area to obtain a photosensitive surface with a preset shape and area. The actual required shape and area can be determined according to the jitter distribution of the Raman scattered light.

[0398] For example, Figure 16 A schematic diagram of a photosensitive surface obtained by arranging a mask plate on an initial photosensitive surface according to an embodiment of the present disclosure is shown schematically. Figure 16 The initial photosensitive surface is a square photosensitive surface, and the photosensitive surface is a circular photosensitive surface.

[0399] According to an embodiment of the present disclosure, the intensity distribution of the light spot of the incident light irradiated to the measurement area is uniform.

[0400] According to an embodiment of the present disclosure, in order to enable the measured object to perform tissue component measurement under more relaxed requirements, thereby better improving the possibility of obtaining a real measured tissue component signal, a mode of ensuring that the intensity distribution of the light spot of the incident light irradiated to the measurement region is uniform can be adopted. Meanwhile, the more uniform the intensity distribution of the light spot of the incident light irradiated to the measurement region, the lower the requirement for the reproducibility of the controllable measurement condition, the better the effect of suppressing the influence of the uncontrollable measurement condition on the measurement result by using the differential measurement method, and thus the reliability of the measurement result can be better ensured. In addition, since the measure of making the intensity distribution of the light spot of the incident light on the measurement region uniform will attenuate the light energy of the incident light to a certain extent, and the tissue component measurement requires that the light energy of the incident light cannot be too small, therefore, it is necessary to try to ensure that the intensity distribution of the light spot of the incident light on the measurement region is uniform, and at the same time, the attenuation of the light energy of the incident light is as small as possible. In addition, if the incident light is realized by using the optical fiber transmission mode, making the distribution of the light spot of the incident light on the measurement region uniform also reduces the adverse effects of the optical fiber jitter on the measurement result.

[0401] According to an embodiment of the present disclosure, the area of the light spot of the incident light irradiated to the measurement region is greater than or equal to a light spot area threshold.

[0402] According to an embodiment of the present disclosure, in order to enable the measured object to perform tissue component measurement under more relaxed requirements, thereby better ensuring the reliability of the measurement result, a mode of making the area of the light spot of the incident light irradiated to the measurement region greater than or equal to a light spot area threshold can be adopted. Meanwhile, within a certain range, the greater the area of the light spot of the incident light irradiated to the measurement region, the lower the requirement for the reproducibility of the controllable measurement condition, the better the effect of suppressing the influence of the uncontrollable measurement condition on the measurement result by using the differential measurement method, and thus the reliability of the measurement result can be better ensured. The light spot area threshold can be set according to actual conditions, which is not limited here. In addition, if the incident light is realized by using the optical fiber transmission mode, making the area of the light spot of the incident light irradiated to the measurement region greater than or equal to the light spot area threshold also reduces the adverse effects of the optical fiber jitter on the measurement result.

[0403] It should be noted that in order to improve the possibility of obtaining a real measured tissue component signal, the following three aspects need to be ensured as much as possible: first, having the ability to perceive the expected change in tissue component concentration; second, minimizing the adverse effects of the uncontrollable measurement condition on the measurement result; and third, ensuring the reproducibility of the controllable measurement condition. The technical solution provided by the embodiment of the present disclosure ensures the above three aspects.

[0404] The measuring device for measuring tissue components has the ability to perceive the expected change in the concentration of the tissue components, and high stability and efficiency of receiving the emitted light are achieved by using a large-area photosensitive surface. The influence of the change in uncontrollable measurement conditions on the measurement results is reduced by using a differential measurement method. The controllable measurement conditions are controlled by using an effective control method.

[0405] Figure 17 A block diagram of a Raman scattering-based tissue component measuring device according to an embodiment of the present disclosure is schematically shown.

[0406] As shown in Figure 17 The tissue component measuring device 1600 includes a light source module 1610, a collection module 1620, and a processing module 1630.

[0407] The light source module 1610 is configured to irradiate a measurement region with incident light of a first preset wavelength. The incident light of the first preset wavelength forms at least one beam of Raman scattered light of a second preset wavelength after passing through the measurement region and being emitted from an emission position. The wavelength difference between the first preset wavelength and the second preset wavelength is determined according to a preset Raman shift.

[0408] The collection module 1620 is configured to acquire Raman intensity corresponding to each beam of Raman scattered light collected by a measurement probe 1640. The tissue component measuring device provided with the measurement probe has a signal-to-noise ratio level that meets the requirement of distinguishing the expected change in the concentration of the tissue components.

[0409] The processing module 1630 is configured to determine the concentration of the measured tissue components according to at least one Raman intensity corresponding to the second preset wavelength.

[0410] According to the technical solution of the embodiment of the present disclosure, the measurement region is irradiated with incident light of a first preset wavelength. The incident light of the first preset wavelength forms at least one beam of Raman scattered light of a second preset wavelength after passing through the measurement region and being emitted from an emission position. The wavelength difference between the first preset wavelength and the second preset wavelength is determined according to a preset Raman shift. The Raman intensity corresponding to each beam of Raman scattered light collected by a measurement probe is acquired. The tissue component measuring device provided with the measurement probe has a signal-to-noise ratio level that meets the requirement of distinguishing the expected change in the concentration of the tissue components. The concentration of the measured tissue components is determined according to at least one Raman intensity corresponding to the second preset wavelength. Since the tissue component measuring device provided with the measurement probe has the signal-to-noise ratio level that meets the requirement of distinguishing the expected change in the concentration of the tissue components, the device has the ability to perceive the expected change in the concentration of the tissue components, thereby improving the possibility of acquiring the real signal of the measured tissue components.

[0411] According to the embodiment of the present disclosure, the tissue component measuring device 1600 can further include a time-gating module configured to shield fluorescent interference.

[0412] According to embodiments of this disclosure, the same incident light beam is irradiated to different incident positions by a beam splitting method.

[0413] According to an embodiment of this disclosure, the measuring probe 1640 includes M photosensitive surfaces.

[0414] The acquisition module 1620 includes an acquisition unit. The acquisition unit is used to acquire the light intensity values ​​corresponding to each Raman scattered light beam collected by M photosensitive surfaces, obtaining T Raman intensities. Each Raman intensity is obtained by processing the light intensity values ​​of the Raman scattered light collected by one or more photosensitive surfaces. The total area of ​​similar photosensitive surfaces is greater than or equal to an area threshold, and the area of ​​each photosensitive surface in the same category is continuous. The similar photosensitive surfaces include one or more photosensitive surfaces, and are used to output a Raman intensity, 1 ≤ T ≤ M, so that the tissue composition measurement device has a signal-to-noise ratio level sufficient to resolve expected changes in tissue component concentration.

[0415] According to embodiments of this disclosure, each photosensitive surface can collect the light intensity value of Raman scattered light emitted from the emission position within a preset anti-shake range corresponding to the photosensitive surface.

[0416] According to embodiments of this disclosure, the average optical path of the Raman scattered light received by each photosensitive surface in the target tissue layer is greater than or equal to a proportion threshold, wherein the total optical path is the total distance the Raman scattered light travels within the measurement area.

[0417] According to embodiments of this disclosure, the total area of ​​similar photosensitive surfaces is determined based on the tissue structure characteristics within the measurement area.

[0418] According to embodiments of this disclosure, the ratio of the area of ​​each photosensitive surface to the photosensitive perimeter of the photosensitive surface is greater than or equal to a ratio threshold.

[0419] According to embodiments of this disclosure, the ratio threshold is greater than or equal to 0.04 mm.

[0420] According to embodiments of this disclosure, the photosensitive surface may be in contact with or not in contact with the surface of the measurement area.

[0421] According to embodiments of this disclosure, the distance between the photosensitive surface and the surface of the measurement area is less than or equal to a first distance threshold, and the efficiency of the photosensitive surface in receiving Raman scattered light is greater than or equal to an efficiency threshold.

[0422] According to embodiments of this disclosure, each photosensitive surface includes an annular photosensitive surface or a non-annular photosensitive surface, and the shapes of different photosensitive surfaces may be the same or different.

[0423] According to embodiments of this disclosure, the non-annular photosensitive surface includes a fan-shaped photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface.

[0424] According to embodiments of this disclosure, the polygonal photosensitive surface includes a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

[0425] According to embodiments of this disclosure, similar photosensitive surfaces include annular photosensitive surfaces or non-annular photosensitive surfaces.

[0426] According to embodiments of this disclosure, a type of photosensitive surface being an annular photosensitive surface includes: when the type of photosensitive surface includes one photosensitive surface, the type of photosensitive surface is an independent annular photosensitive surface; when the type of photosensitive surface includes multiple photosensitive surfaces, the type of photosensitive surface is an annular photosensitive surface formed by combining multiple photosensitive surfaces. A type of photosensitive surface being a non-annular photosensitive surface includes: when the type of photosensitive surface includes one photosensitive surface, the type of photosensitive surface is an independent non-annular photosensitive surface; when the type of photosensitive surface includes multiple photosensitive surfaces, the type of photosensitive surface is a non-annular photosensitive surface formed by combining multiple photosensitive surfaces.

[0427] According to embodiments of this disclosure, when it is determined that the distance between a similar photosensitive surface and the target area is greater than or equal to a second distance threshold, the similar photosensitive surface includes an annular photosensitive surface, a fan-shaped photosensitive surface, a fan-shaped photosensitive surface, a circular photosensitive surface, or a square photosensitive surface.

[0428] According to embodiments of this disclosure, when it is determined that the distance between similar photosensitive surfaces and the target area is less than or equal to a third distance threshold, the shape of the similar photosensitive surfaces is determined based on the jitter distribution of Raman scattered light.

[0429] According to embodiments of this disclosure, the jitter distribution of Raman scattered light includes a jitter distribution along a first direction and a jitter distribution along a second direction, wherein the first direction and the second direction are perpendicular to each other, and the ratio of the length of the same photosensitive surface along the first direction to the length of the same photosensitive surface along the second direction is determined based on the ratio of the jitter amplitude of Raman scattered light along the first direction to the jitter amplitude of Raman scattered light along the second direction, wherein the jitter amplitude of Raman scattered light along the first direction is the largest.

[0430] According to embodiments of this disclosure, similar photosensitive surfaces include rectangular photosensitive surfaces or elliptical photosensitive surfaces. The ratio of the length to the width of the rectangular photosensitive surface is determined based on the ratio of the dithering amplitude of the Raman scattered light along the first direction to the dithering amplitude of the Raman scattered light along the second direction. The ratio of the major axis to the minor axis of the elliptical photosensitive surface is determined based on the ratio of the dithering amplitude of the Raman scattered light along the first direction to the dithering amplitude of the Raman scattered light along the second direction.

[0431] According to embodiments of this disclosure, the angle between each portion of the photosensitive surface and the direction of the corresponding incident light is greater than or equal to 0° and less than or equal to 360°.

[0432] According to embodiments of this disclosure, each portion of the photosensitive surface forms an angle greater than or equal to 0° and less than or equal to 360° with respect to the direction of the corresponding incident light, thereby achieving diffuse measurement. According to embodiments of this disclosure, a suitable location for the photosensitive surface can be determined based on wavelength characteristics and / or measurement area characteristics, wherein the wavelength characteristics may include the penetration depth of the wavelength, and the measurement area characteristics may include the thickness of the measurement area. Optionally, the angle between each portion of the photosensitive surface and the direction of the corresponding incident light can typically be set to a preset angle.

[0433] For example, if the wavelength has a deep penetration depth and / or the measurement area is thin, the position of the photosensitive surface can be set to be on the opposite side of the measurement area to the incident position of the corresponding incident light. If the wavelength has a shallow penetration depth and / or the measurement area is thick, the position of the photosensitive surface can be set to be on the same side of the measurement area to the incident position of the corresponding incident light.

[0434] For example, Figure 18 A schematic diagram of a diffuse measurement according to an embodiment of the present disclosure is shown. Figure 19 The angle between the photosensitive surface C and the incident light is 90°. The photosensitive surface D is located on the same side of the measurement area as the incident light, while the photosensitive surface E is located on the opposite side of the measurement area as the incident light.

[0435] According to embodiments of this disclosure, the processing module 1630 includes a processing unit. The processing unit is configured to process at least one Raman intensity corresponding to a second preset wavelength based on an interference suppression method to determine the concentration of the measured tissue component.

[0436] According to embodiments of this disclosure, among the M photosensitive surfaces, there are one or more similar photosensitive surfaces corresponding to a second preset wavelength. The similar photosensitive surfaces are used to collect a first Raman intensity and / or a second Raman intensity corresponding to the second preset wavelength at different times. The first Raman intensity is the light intensity during the contraction period, and the second Raman intensity is the light intensity during the relaxation period. The similar photosensitive surfaces include one or more photosensitive surfaces.

[0437] The processing unit is used to determine the concentration of the component of the tissue being tested based on the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength.

[0438] According to an embodiment of this disclosure, among the M photosensitive surfaces, there are a first similar photosensitive surface and a second similar photosensitive surface corresponding to a second preset wavelength. The first similar photosensitive surface is used to collect a first Raman intensity corresponding to the second preset wavelength, and the second similar photosensitive surface is used to collect a second Raman intensity corresponding to the second preset wavelength. The first similar photosensitive surface includes one or more photosensitive surfaces, and the second similar photosensitive surface includes one or more photosensitive surfaces.

[0439] The processing unit is used to determine the concentration of the component of the tissue being tested based on the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength.

[0440] According to embodiments of this disclosure, the first and second similar photosensitive surfaces are the same type of photosensitive surface, and the Raman scattered light received by the first and second similar photosensitive surfaces is obtained by incident light entering from different incident positions and being transmitted.

[0441] According to embodiments of this disclosure, the first similar photosensitive surface and the second similar photosensitive surface are different similar photosensitive surfaces.

[0442] According to an embodiment of this disclosure, the average optical path of the Raman scattered light received at different photosensitive positions of each photosensitive surface in the first type of photosensitive surface belongs to a first average optical path range, wherein the first average optical path range is determined based on a first average optical path value, which is an average value calculated based on the average optical path of the Raman scattered light received at each photosensitive position of the first type of photosensitive surface.

[0443] The average optical path length of the Raman scattered light received at different photosensitive positions of each photosensitive surface in the second type of photosensitive surface belongs to the second average optical path length range. The second average optical path length range is determined based on the second average optical path length, which is the average value calculated based on the average optical path length of the Raman scattered light received at each photosensitive position of the second type of photosensitive surface.

[0444] According to embodiments of this disclosure, the absolute value of the difference between the first optical path average value and the second optical path average value falls within the range of the first optical path difference.

[0445] According to embodiments of this disclosure, a first average optical path range is less than or equal to a first optical path difference range, and a second average optical path range is less than or equal to the first optical path difference range.

[0446] According to embodiments of this disclosure, the first optical path difference range is determined based on the optimal differential optical path corresponding to the second preset wavelength.

[0447] According to an embodiment of this disclosure, the source-detection distance of each photosensitive surface in the first similar photosensitive surface corresponding to the second preset wavelength from the center of the incident light is within a preset source-detection distance range corresponding to the second preset wavelength, wherein the preset source-detection distance range is determined based on the source-detection distance of the floating reference position corresponding to the second preset wavelength from the center of the incident light.

[0448] According to an embodiment of this disclosure, among the M photosensitive surfaces, there are similar photosensitive surfaces corresponding to a second preset wavelength. The similar photosensitive surfaces are used to collect a third Raman intensity corresponding to the second preset wavelength, and the similar photosensitive surfaces include one or more photosensitive surfaces.

[0449] The processing unit is used to determine the concentration of the component of the tissue being tested based on the third Raman intensity corresponding to the second preset wavelength.

[0450] According to embodiments of this disclosure, the difference between the average optical path of the Raman scattered light received at different photosensitive positions of each photosensitive surface in the same type and the optimal optical path corresponding to the second preset wavelength belongs to the second optical path difference range.

[0451] According to embodiments of this disclosure, different portions of the same photosensitive surface may be on the same plane or on different planes.

[0452] According to embodiments of this disclosure, the photosensitive surface can be a planar photosensitive surface or a three-dimensional photosensitive surface. If different portions of the photosensitive surface are all on the same plane, then the photosensitive surface is a planar photosensitive surface. If different portions of the photosensitive surface are on different planes, then the photosensitive surface is a three-dimensional photosensitive surface. The specific choice between a planar or three-dimensional photosensitive surface can be determined based on actual circumstances and is not specifically limited herein.

[0453] Optionally, for contact measurements, to improve measurement accuracy, it is necessary to ensure that the target surface of the photosensitive surface and the skin surface of the measurement area are in good contact. Here, the target surface of the photosensitive surface refers to the surface close to the measurement area. Since the flatness of the skin surface in the measurement area may not be high, using a planar photosensitive surface may make it difficult to achieve good contact between the target surface of the photosensitive surface and the skin surface of the measurement area. A three-dimensional photosensitive surface, however, has different parts located on different planes; therefore, a three-dimensional photosensitive surface can be used, and its specific form can be set according to the tissue structure characteristics of the measurement area.

[0454] Figure 20 A schematic diagram of a three-dimensional photosensitive surface in the form of a glove according to an embodiment of the present disclosure is shown. Figure 21 A schematic diagram of a stereoscopic photosensitive surface in the form of another glove according to an embodiment of the present disclosure is shown.

[0455] Figure 22 A schematic diagram of a three-dimensional photosensitive surface in the form of a bracelet according to an embodiment of the present disclosure is shown. Figure 22 A schematic diagram of a stereoscopic photosensitive surface in another form of wristband according to an embodiment of the present disclosure is shown.

[0456] Figure 22 A schematic diagram of a stereoscopic photosensitive surface for arm measurement according to an embodiment of the present disclosure is shown. Figure 23 In this system, the distance between different parts of the photosensitive surface and the preset plane can be set according to the tissue structure characteristics of the arm. Figure 23 In the equation, h1 and h2 represent the distances from different parts of the photosensitive surface to the preset plane.

[0457] According to embodiments of this disclosure, the photosensitive surfaces are arranged in the same plane or different planes, wherein the photosensitive surface set includes multiple photosensitive surfaces.

[0458] According to embodiments of this disclosure, each photosensitive surface included in the photosensitive surface set can be a planar photosensitive surface or a three-dimensional photosensitive surface. If the photosensitive surface set includes multiple planar photosensitive surfaces, the photosensitive surface form presented by the photosensitive surface set can be a three-dimensional photosensitive surface by setting some or all of these multiple planar photosensitive surfaces on different planes.

[0459] It should be noted that the above-mentioned effect for contact measurement can also be achieved by using a three-dimensional photosensitive surface formed by multiple planar photosensitive surfaces, which will not be elaborated on here.

[0460] According to embodiments of this disclosure, the anodes of different photosensitive surfaces among the M photosensitive surfaces are not electrically connected to each other, the anodes of some photosensitive surfaces are electrically connected, or the anodes of all photosensitive surfaces are electrically connected.

[0461] According to embodiments of this disclosure, each of the M photosensitive surfaces can be used independently, in which case the anodes of different photosensitive surfaces among the M photosensitive surfaces are not electrically connected.

[0462] Some of the M photosensitive surfaces can be used in combination, in which case the anodes of the different photosensitive surfaces used in combination are electrically connected.

[0463] All of the M photosensitive surfaces can be used in combination, in which case the anodes of the different photosensitive surfaces used in combination are electrically connected.

[0464] According to embodiments of this disclosure, Figure 24 A schematic diagram illustrating the anode electrical connection of a different photosensitive surface according to an embodiment of the present disclosure is shown. Figure 24 As shown, the anodes of all photosensitive surfaces are electrically connected.

[0465] According to embodiments of this disclosure, the light source module includes a light source unit. The light source unit is used to illuminate the measurement area with incident light of a first preset wavelength while satisfying reproducibility under controllable measurement conditions.

[0466] According to embodiments of this disclosure, the tissue composition measuring device 1600 may further include a first determining module, a second determining module, and a setting module. The first determining module is used to determine positioning features. The second determining module is used to determine a measurement area based on the positioning features, wherein the measurement area is a reproducible area that satisfies controllable measurement conditions. The setting module is used to set the measuring probe at a position corresponding to the measurement area.

[0467] According to embodiments of this disclosure, the positioning features include first posture positioning features and regional positioning features.

[0468] The second determining module may include a first adjustment unit and a first determining unit. The first adjustment unit is used to adjust the current measurement posture of the object being measured to a target measurement posture based on the first posture positioning features. The first determining unit is used to determine the measurement area based on the area positioning features when the current measurement posture is the target measurement posture.

[0469] like Figure 25 As shown, according to an embodiment of the present disclosure, the tissue composition measuring device 1600 may further include a fixing part 1650, which is used to set the measuring probe 1640 at a position corresponding to the measuring area. The fixing part 1650 and the measuring probe 1640 may be integral, partially separate, or completely separate.

[0470] According to embodiments of this disclosure, Figure 26 The fixing part 1650 and the measuring probe 1640 can be integrated or separate.

[0471] like Figure 26 As shown, according to an embodiment of this disclosure, the fixing part 1650 includes a fixing base 1651 and a first mating member 1652. The first mating member 1652 is used to position the fixing base 1651 at a position corresponding to the measurement area. The fixing base 1651 is used to fix the measuring probe 1640.

[0472] According to an embodiment of this disclosure, the hardness of the first mating part 1652 includes a first hardness and a second hardness, wherein the first hardness is less than the second hardness. The first hardness is the hardness corresponding to the process of fixing the first mating part 1652 to the fixing seat 1651, and the second hardness is the hardness corresponding to the first mating part 1652 after fixing the fixing seat 1651.

[0473] According to embodiments of this disclosure, in order for the first mating member 1652 to effectively fix the fixing seat 1651, the first mating member 1652 needs to be relatively rigid. At the same time, in order to minimize the impact of the first mating member 1652 fixing the fixing seat 1651, the first mating member 1652 also needs to have a certain degree of flexibility. Therefore, the above-mentioned requirements place on the rigidity of the first mating member 1652.

[0474] To solve the above problems, the hardness of the first mating part 1652 can be changed. Specifically, the hardness of the first mating part 1652 includes a first hardness and a second hardness. The first hardness represents the hardness corresponding to the process of fixing the first mating part 1652 to the fixing seat 1651, and the second hardness represents the hardness corresponding to the condition after the first mating part 1652 is fixed to the fixing seat 1651. The first hardness is less than the second hardness. This approach can ensure that the first mating part 1652 can effectively perform its fixing function while minimizing the impact of the first mating part 1652 fixing the fixing seat 1651.

[0475] According to embodiments of this disclosure, the first mating element 1652 includes a first Velcro strap or a first elastic band.

[0476] For example, Figure 27 A schematic diagram of a first mating member according to an embodiment of the present disclosure is shown. Figure 27 The first mating part 1652 is a hook and loop fastener. Because the textured surface of the hook and loop fastener is very soft, it reduces the impact when the first mating part 1652 fixes the fixing seat 1651. At this point, the hardness of the first mating part 1652 is at its first hardness. Simultaneously, to ensure its fixing function, after the first mating part 1652 fixes the fixing seat 1651, the hook side can be glued to the textured surface, increasing the hardness of the first mating part 1652. At this point, the hardness of the first mating part 1652 is at its second hardness.

[0477] According to the embodiments of this disclosure, since the hardness corresponding to the first mating member 1652 fixing the fixing seat 1651 during the process is the first hardness, it can reduce the influence generated when the first mating member 1652 fixes the fixing seat 1651. Therefore, it can ensure as much as possible that the skin condition of the skin in the measurement area meets the first preset condition during the process of setting the fixing seat 1651 in the position corresponding to the measurement area by the first mating member 1652.

[0478] According to an embodiment of this disclosure, the hardness of the first mating part 1652 is greater than or equal to a first hardness threshold and less than or equal to a second hardness threshold.

[0479] According to embodiments of this disclosure, in order to meet the hardness requirements of the first mating part 1652, in addition to the methods described above, the first mating part 1652 can also be made of a material with a hardness greater than or equal to a first hardness threshold and less than or equal to a second hardness threshold. This also ensures that the first mating part 1652 can fix the fixing seat 1651, while minimizing the impact of the first mating part 1652 fixing the fixing seat 1651. It should be noted that the first hardness threshold and the second hardness threshold can be set according to actual conditions and are not specifically limited here.

[0480] like Figure 27 As shown, according to an embodiment of the present disclosure, the tissue composition measuring device 1600 may further include a first magnetic part 1660, all or part of the first mating member 1652 being a metal hinge, and the first magnetic part 1660 mating with the first mating member 1652 to fix the fixing base 1651.

[0481] According to the embodiments of this disclosure, in order to meet the hardness requirements of the first mating member 1652, in addition to the method described above, the first mating member 1652 can also be made entirely or partially of a metal hinge. This can also achieve the same effect of fixing the first mating member 1652 to the fixing seat 1651, and minimize the impact of the first mating member 1652 fixing the fixing seat 1651.

[0482] The fixing function is achieved as follows: After the first mating part 1652 fixes the fixing base 1651, the first magnetic part 1660 can be attracted to the first mating part 1652, so that the first magnetic part 1660 cooperates with the first mating part 1652 to fix the fixing base 1651. This achieves the fixing function. (See also...) Figure 27 . Figures 28-29 A schematic diagram of another first mating member according to an embodiment of the present disclosure is shown. Figure 28 The first mating component 1652 is entirely made of metal hinges. After the first mating component 1652 has secured the fixing base 1651, the first magnetic part 1660 can be attracted to the first mating component 1652. The first magnetic part 1660 can be a miniature electromagnet.

[0483] Furthermore, since metal hinges are ferromagnetic metals, and metals readily absorb heat, direct contact between the hinge and skin can significantly affect skin temperature. Therefore, to avoid the impact of heat absorption on skin temperature, a heat-insulating material can be placed under the metal hinge. Optionally, the heat-insulating material can be velvet.

[0484] The above is possible because the metal hinge has good flexibility, thus reducing the impact when the first mating part 1652 fixes the fixing seat 1651. Simultaneously, after the first mating part 1652 has fixed the fixing seat 1651, the first magnetic part 1660 adsorbed on the first mating part 1652 makes the first mating part 1652 more rigid, thus achieving the fixing effect.

[0485] It should be noted that since all or part of the first mating member 1652 is a metal hinge, and the metal hinge has good flexibility, it can reduce the impact of the first mating member 1652 fixing the fixing seat 1651. Therefore, it can ensure as much as possible that the skin condition of the skin in the measurement area meets the first preset condition when the fixing seat 1651 is set in the position corresponding to the measurement area by the first mating member 1652.

[0486] According to an embodiment of this disclosure, the surface of the first mating member 1652 is provided with a hole.

[0487] According to embodiments of this disclosure, the measuring probe 1640 is fixed to the mounting base 1651 by at least one of the following methods: the measuring probe 1640 is fixed to the mounting base 1651 with tape; the measuring probe 1640 is fixed to the mounting base 1651 with fasteners; or the measuring probe 1640 is fixed to the mounting base 1651 by magnetic force; and the coefficient of friction between the measuring probe 1640 and the mounting base 1651 is greater than or equal to a friction coefficient threshold.

[0488] According to embodiments of this disclosure, in order to fix the measuring probe 1640 to the fixing base 1651 and ensure that the measuring probe 1640 does not move in the fixing base 1651, at least one of the following methods can be adopted.

[0489] Method 1: The measuring probe 1640 can be fixed to the mounting base 1651 using tape. Method 2: The measuring probe 1640 can be fixed to the mounting base 1651 using fasteners. Method 3: The measuring probe 1640 can be fixed to the mounting base 1651 using magnetism. Method 4: The coefficient of friction between the measuring probe 1640 and the mounting base 1651 is greater than or equal to a friction coefficient threshold. Optionally, the mounting base 1651 can be made of rubber, aluminum, or plastic.

[0490] According to an embodiment of this disclosure, the fixing part 1650 includes a second mating member. The second mating member is used to position the measuring probe 1640 at a position corresponding to the measuring area.

[0491] According to an embodiment of this disclosure, the hardness of the second mating component includes a third hardness and a fourth hardness, wherein the third hardness is less than the fourth hardness. The third hardness is the hardness corresponding to the process of fixing the measuring probe 1640 in the second mating component, and the fourth hardness is the hardness corresponding to the second mating component after fixing the measuring probe 1640.

[0492] According to embodiments of this disclosure, the second mating component includes a second Velcro strap or a second elastic band.

[0493] According to embodiments of this disclosure, the hardness of the second mating component is greater than or equal to a third hardness threshold and less than or equal to a fourth hardness threshold.

[0494] According to embodiments of this disclosure, the tissue composition measuring device 1600 may further include a second magnetic part, all or part of the second mating member being a metal hinge, and the second magnetic part cooperating with the second mating member to fix the measuring probe 1640.

[0495] According to an embodiment of this disclosure, the surface of the second mating member is provided with holes.

[0496] According to the embodiments of this disclosure, the relevant description of the second mating component can be found in the above description of the first mating component 1652, and will not be repeated here. The difference is that the second mating component is used to fix the measuring probe 1640.

[0497] According to embodiments of this disclosure, a first determining unit is configured to: acquire a first projection feature; if the determined area positioning feature does not match the first projection feature, adjust the position of the measuring probe 1640 and / or the fixing part 1650 until the area positioning feature matches the first projection feature; if the determined area positioning feature matches the first projection feature, determine the area corresponding to the measuring probe 1640 and / or the fixing part 1650 as the measuring area.

[0498] like Figure 28 As shown, according to an embodiment of the present disclosure, the tissue composition measuring device 1600 may further include a region positioning part 1670, which is disposed on the object to be measured, the measuring probe 1640, the fixing part 1650 or other objects, and the region positioning part 1670 is used to project a first projection feature.

[0499] According to embodiments of this disclosure, Figure 29 A schematic diagram of a region positioning unit according to an embodiment of the present disclosure is shown. Figure 29 The measuring probe 1640 and the fixing part 1650 are not shown. The area positioning part 1670 is used to project a first projection feature, which is a crosshair light spot. The area positioning feature is a crosshair marker point.

[0500] Figure 30 A schematic diagram of another area positioning unit according to an embodiment of the present disclosure is shown. Figure 30 The central positioning unit 1670 is integrated with the measuring probe 1640 and the fixing unit 1650, and the regional positioning feature is set on the back of the hand of the object being measured. The regional positioning unit 1670 is used to project a first projection feature, which is a crosshair light spot.

[0501] According to embodiments of this disclosure, when it is determined that the area positioning unit 1670 is provided on the measuring probe 1640, the area positioning feature is not provided on the measuring probe 1640. When it is determined that the area positioning feature is provided on the fixing unit 1650, the area positioning feature is not provided on the fixing unit 1650.

[0502] According to an embodiment of this disclosure, the area positioning unit 1670 includes a first laser.

[0503] According to embodiments of this disclosure, a first laser can project a light spot of a preset shape to form a first projection feature.

[0504] According to embodiments of this disclosure, a first determining unit is configured to: acquire a first target image; acquire a first template image, wherein the first template image includes region positioning features; if it is determined that the first target image and the first template image do not match, adjust the position of the measuring probe 1640 and / or the fixing part 1650 to acquire a new first target image until the new first target image matches the first template image; if it is determined that the first target image matches the first template image, determine the region corresponding to the measuring probe 1640 and / or the fixing part 1650 as a measurement region.

[0505] like Figure 30 As shown, according to an embodiment of the present disclosure, the tissue composition measuring device 1600 may further include a first image acquisition unit 1680, which is disposed on the object to be measured, the measuring probe 1640, the fixing part 1650 or other objects, and is used to acquire a first target image.

[0506] According to embodiments of this disclosure, Figure 31 A schematic diagram of a first image acquisition unit according to an embodiment of the present disclosure is shown. Figure 32 The first image acquisition unit 1680 is integrated with the measuring probe 1640 and the fixing unit 1650, and the area positioning feature is set on the back of the hand of the object being measured. The first image acquisition unit 1680 is used to acquire the first target image. The first image acquisition unit 1680 can be an image sensor.

[0507] According to embodiments of this disclosure, a first determining unit is configured to: acquire a second target image, wherein the second target image includes region positioning features. If the position of the region positioning features in the second target image is determined not to be a first preset position, the position of the measuring probe 1640 and / or the fixing part 1650 is adjusted to acquire a new second target image until the position of the region positioning features in the new second target image is the first preset position. If the position of the region positioning features in the new second target image is determined to be the first preset position, the region corresponding to the measuring probe 1640 and / or the fixing part 1650 is determined as a measuring region.

[0508] According to embodiments of this disclosure, the tissue composition measuring device 1600 may further include a second image acquisition unit disposed on the object to be measured, the measuring probe 1640, the fixing part 1650 or other objects, and the second image acquisition unit is used to acquire a second target image.

[0509] According to embodiments of this disclosure, when it is determined that the second image acquisition unit is disposed on the measuring probe 1640, the area positioning feature is not disposed on the measuring probe 1640. When it is determined that the second image acquisition unit is disposed on the fixing part 1650, the area positioning feature is not disposed on the fixing part 1650.

[0510] According to embodiments of this disclosure, a first adjustment unit is configured to: acquire a second projection feature; adjust the current measurement posture until the first posture positioning feature matches the second projection feature if a mismatch is determined between the first posture positioning feature and the second projection feature; and determine the current measurement posture as the target measurement posture if a match is determined between the first posture positioning feature and the second projection feature.

[0511] like Figure 32 As shown, according to an embodiment of the present disclosure, the tissue composition measuring device 1600 may further include a first posture positioning part 1690, which is disposed on the object to be measured, the measuring probe 1640, the fixing part 1650 or other objects, and the first posture positioning part 1690 is used to project a second projection feature.

[0512] According to embodiments of this disclosure, when it is determined that the first posture positioning part 1690 is disposed on the measuring probe 1640, the first posture positioning feature is not disposed on the measuring probe 1640. When it is determined that the first posture positioning part 1690 is disposed on the fixing part 1650, the first posture positioning feature is not disposed on the fixing part 1650.

[0513] According to an embodiment of this disclosure, the first posture positioning unit 1690 includes a second laser.

[0514] According to embodiments of this disclosure, the second laser can project a light spot of a preset shape to form a second projection feature.

[0515] According to embodiments of this disclosure, a first adjustment unit is configured to: acquire a third target image; acquire a second template image, wherein the second template image includes first pose localization features; if it is determined that the third target image and the second template image do not match, adjust the current measurement pose to acquire a new third target image until the new third target image matches the second template image; if it is determined that the new third target image matches the second template image, determine the current measurement pose as the target measurement pose.

[0516] like Figure 32As shown, according to an embodiment of the present disclosure, the tissue composition measuring device 1600 may further include a third image acquisition unit 1700, which is disposed on the object to be measured, the measuring probe 1640, the fixing part 1650 or other objects, and is used to acquire a third target image.

[0517] According to embodiments of this disclosure, Figure 33 A schematic diagram of a third image acquisition unit according to an embodiment of the present disclosure is shown. Figure 34 The third image acquisition unit 1700 is integrated with the measuring probe 1640 and the fixing unit 1650, and the first posture positioning feature is set on the back of the hand of the object being measured. The third image acquisition unit 1700 is used to acquire a third target image. The third image acquisition unit 1700 can be an image sensor.

[0518] According to embodiments of this disclosure, a first adjustment unit is configured to: acquire a fourth target image, wherein the fourth target image includes a first pose localization feature; if it is determined that the position of the first pose localization feature in the fourth target image is not at a second preset position, adjust the current measurement pose to acquire a new fourth target image until the position of the first pose localization feature in the new fourth target image is at the second preset position; if it is determined that the position of the first pose localization feature in the new fourth target image is at the second preset position, determine the current measurement pose as the target measurement pose.

[0519] According to embodiments of the present disclosure, the tissue composition measuring device 1600 may further include a fourth image acquisition unit, which is disposed on the object to be measured, the measuring probe 1640, the fixing part 1650 or other objects, and is used to acquire a fourth target image.

[0520] According to embodiments of this disclosure, when it is determined that the fourth image acquisition unit is disposed on the measuring probe 1640, the first posture positioning feature is not disposed on the measuring probe 1640. When it is determined that the fourth image acquisition unit is disposed on the fixing part 1650, the first posture positioning feature is not disposed on the fixing part 1650.

[0521] According to embodiments of this disclosure, the tissue composition measuring device 1650 may further include a third determining module and an adjusting module. The third determining module is used to determine a second posture positioning feature if the measuring probe 1640 is positioned at a location corresponding to the measuring area, and the current measuring posture is not the target measuring posture. The adjusting module is used to adjust the current measuring posture to the target measuring posture based on the second posture positioning feature.

[0522] According to embodiments of this disclosure, the adjustment module may include a first acquisition unit, a second adjustment unit, and a second determination unit.

[0523] The first acquisition unit is used to acquire the third projection feature. The second adjustment unit is used to adjust the current measurement posture until the second posture positioning feature matches the third projection feature if it is determined that the second posture positioning feature and the third projection feature do not match. The second determination unit is used to determine the current measurement posture as the target measurement posture if it is determined that the second posture positioning feature and the third projection feature match.

[0524] According to embodiments of the present disclosure, the tissue composition measuring device 1600 may further include a second posture positioning part disposed on the object being measured, the measuring probe 1640, the fixing part 1650 or other objects, and the second posture positioning part is used to project a third projection feature.

[0525] According to embodiments of this disclosure, when it is determined that the second posture positioning part is disposed on the measuring probe 1640, the second posture positioning feature is not disposed on the measuring probe 1640 and the fixing part 1650. When it is determined that the second posture positioning part is disposed on the fixing part 1650, the second posture positioning feature is not disposed on the measuring probe 1640 and the fixing part 1650.

[0526] According to embodiments of this disclosure, the second posture positioning unit includes a third laser.

[0527] According to embodiments of this disclosure, a third laser can project a light spot of a preset shape to form a third projection feature.

[0528] According to embodiments of this disclosure, the adjustment module may include a second acquisition unit, a third acquisition unit, a third adjustment unit, and a third determination unit. The second acquisition unit is used to acquire a fifth target image. The third acquisition unit is used to acquire a third template image, wherein the third template image includes second pose localization features. The third adjustment unit is used to adjust the current measurement pose to acquire a new fifth target image when it is determined that the fifth target image and the third template image do not match, until the new fifth target image matches the third template image. The third determination unit is used to determine the current measurement pose as the target measurement pose when it is determined that the new fifth target image matches the third template image.

[0529] According to embodiments of this disclosure, the tissue composition measuring device may further include a fifth image acquisition unit, which is disposed on the object to be measured, the measuring probe 1640, the fixing part 1650 or other objects, and is used to acquire a fifth target image.

[0530] According to embodiments of this disclosure, the adjustment module may include a fourth acquisition unit, a fourth adjustment unit, and a fourth determination unit. The fourth acquisition unit is used to acquire a sixth target image, wherein the sixth target image includes a second pose localization feature. The fourth adjustment unit is used to adjust the current measurement pose to acquire a new sixth target image when it is determined that the position of the second pose localization feature in the sixth target image is not at a third preset position, until the position of the second pose localization feature in the new sixth target image is at the third preset position. The fourth determination unit is used to determine the current measurement pose as the target measurement pose when it is determined that the position of the second pose localization feature in the new sixth target image is at the third preset position.

[0531] According to embodiments of the present disclosure, the tissue composition measuring device 1600 may further include a sixth image acquisition unit, which is disposed on the object to be measured, the measuring probe 1640, the fixing part 1650 or other objects, and is used to acquire a sixth target image.

[0532] According to an embodiment of this disclosure, when it is determined that the sixth image acquisition unit is disposed on the measuring probe 1640, the second posture positioning feature is not disposed on the measuring probe 1640 and the fixing part 1650.

[0533] According to embodiments of this disclosure, the sixth image acquisition unit, the fifth image acquisition unit, the fourth image acquisition unit, the third image acquisition unit 1700, the first image acquisition unit 1680, and the second image acquisition unit may be different, partially the same, or completely the same.

[0534] According to embodiments of this disclosure, when optical methods are used to locate the measurement area and measurement posture, the area positioning unit 1670, the first posture positioning unit 1690, and the second posture positioning unit can be completely identical, partially identical, or completely different. Partial identity means that two of the three structures are the same. If all three structures are identical, it means that the same structure can be used to generate the first projection feature, the second projection feature, and the third projection feature. This approach simplifies the complexity of the positioning structure.

[0535] When using image matching to locate the measurement area and posture, the first image acquisition unit 1680, the third image acquisition unit 1700, and the fifth image acquisition unit can be all identical, partially identical, or all different. Partial identity means that two of the three structures are the same. If all three structures are identical, then the same structure can be used to generate the first target image, the third target image, and the fifth target image. This method simplifies the complexity of the positioning structure.

[0536] When using imaging methods to locate the measurement area and posture, the second, fourth, and sixth image acquisition units can be all identical, partially identical, or all different. Partial identity means that two of the three structures are the same. If all three structures are identical, then the same structure can be used to generate the second, fourth, and sixth target images. This method simplifies the complexity of the positioning structure.

[0537] The region positioning unit 1670, the first posture positioning unit 1690, and the second posture positioning unit have the same structure. The second posture positioning feature is completely identical to the region positioning feature and partially identical to the first posture positioning feature. The measurement area is the forearm extension side.

[0538] Figure 34 A schematic diagram illustrating a measurement posture and measurement area positioning according to an embodiment of the present disclosure is shown. The area positioning unit 1670, the first posture positioning unit 1690, and the second posture positioning unit each include a laser 1 and a laser 2. Laser 1 and laser 2 are disposed on the measurement probe 1640.

[0539] During the initial posture positioning measurement, the measuring probe 1640 is positioned on the base. Before the initial posture positioning measurement is completed, the position of the measuring probe 1640 remains fixed. Based on the first posture positioning feature and the second projection feature, the current measurement posture is adjusted until the first posture positioning feature matches the second projection feature. When the two match, the initial posture positioning measurement is considered complete.

[0540] When locating the measurement area, the measuring probe 1640 is placed on the object being measured. The position of the measuring probe 1640 is adjusted according to the area positioning features and the first projection features until the area positioning features match the first projection features. When the two match, it indicates that the measurement area location has been completed.

[0541] After the measuring probe 1640 is set on the object being measured, if the current measuring posture is not the target posture, a second measurement posture positioning is required before measurement. Based on the second posture positioning features and the third projection features, the current measuring posture is adjusted until the second posture positioning features and the third projection features match. If they match, the second measurement posture positioning is considered complete.

[0542] The region positioning unit 1670, the first posture positioning unit 1690, and the second posture positioning unit are of the same structure. The region positioning features are exactly the same as the second posture positioning features, and are partially the same as the first posture positioning features. The measurement region is the forearm extension side.

[0543] Figure 35 A schematic diagram illustrating another measurement posture and measurement area positioning according to an embodiment of the present disclosure is shown. Figure 36 The mid-area positioning unit 1670 and the second posture positioning unit both include lasers 3 and 4. The first posture positioning unit 1690 includes lasers 5 and 6. Lasers 3 and 4 are disposed on the measuring probe 1640. Lasers 5 and 6 are disposed on the base.

[0544] According to embodiments of this disclosure, the tissue composition measuring device 1600 may include a prompting module. The prompting module is used to generate prompting information, wherein the prompting information is used to indicate that the measurement posture positioning and / or measurement area positioning is complete, and the prompting information may be in the form of at least one of an image, voice, or vibration.

[0545] According to embodiments of this disclosure, the photosensitive surface is obtained by setting a mask on the initial photosensitive surface, and the transmittance of the mask is less than or equal to a transmittance threshold.

[0546] According to embodiments of this disclosure, the shape of the mask is determined based on the jitter distribution of the Raman scattered light.

[0547] like Figures 38-39 As shown, according to an embodiment of this disclosure, a first sleeve 1710 is provided on the measuring probe 1640. The first end face of the first sleeve 1710 extends beyond the target surface of the measuring probe 1640, wherein the first end face represents the end face close to the measuring area, and the target surface of the measuring probe 1640 represents the surface close to the measuring area.

[0548] According to embodiments of this disclosure, in order to shield interfering light, a first sleeve 1710 can be provided on the measuring probe 1640, such that the end face of the first sleeve 1710 that is close to the measuring area extends beyond the target surface of the measuring probe 1640. Interfering light may include surface reflected light and / or diffracted light.

[0549] According to an embodiment of this disclosure, a scattering material is disposed on the second end face and / or the interior region of the first sleeve 1710, wherein the first end face and the second end face are two opposing end faces, and the interior region includes a portion of the interior region or the entire interior region.

[0550] According to embodiments of this disclosure, in order to ensure a uniform intensity distribution of the light spot illuminating the measurement area, a scattering material can be provided in a corresponding portion of the first sleeve 1710. The scattering material may include sulfuric acid paper, silica gel, or a target mixture, wherein the target mixture may include a mixture of polydimethylsiloxane and titanium dioxide particles.

[0551] like Figure 37As shown, according to an embodiment of the present disclosure, the tissue composition measuring device 1600 further includes a second sleeve 1720 disposed outside the target area of ​​the first sleeve 1710, wherein the target area refers to a portion or all of the first sleeve 1710 extending beyond the target surface of the measuring probe 1640.

[0552] According to embodiments of this disclosure, in order to make the light spot illuminating the measurement area as large as possible, a second sleeve 1720 can be provided outside the target area of ​​the first sleeve 1710.

[0553] According to an embodiment of this disclosure, the second sleeve 1710 is provided with a scattering agent.

[0554] According to an embodiment of this disclosure, if a second sleeve 1710 is provided, in order to make the intensity distribution of the light spot irradiated by the incident light in the measurement area uniform, a scattering object can be provided in a corresponding part of the second sleeve 1710.

[0555] According to embodiments of this disclosure, the inner diameter of the first sleeve is greater than or equal to an inner diameter threshold.

[0556] According to an embodiment of this disclosure, the opening on the first end face of the first sleeve is greater than or equal to the opening on the second end face of the first sleeve.

[0557] According to embodiments of this disclosure, in order to make the light spot irradiated on the measurement area as large as possible, the inner diameter of the first sleeve 1710 can be made greater than or equal to the inner diameter threshold, and / or the opening of the first end face of the first sleeve 1710 can be made greater than or equal to the opening of the second end face of the first sleeve 1710, so that the opening of the end face of the first sleeve 1710 close to the measurement area is greater than or equal to the opening of the end face of the first sleeve 1710 far from the measurement area.

[0558] like Figure 37 As shown, according to an embodiment of this disclosure, a refractive index matching material is filled between the photosensitive surface and the measurement area.

[0559] According to embodiments of this disclosure, since jitter can cause instability on the skin surface of the measurement area, which in turn changes the emission angle of the emitted light and affects the possibility of obtaining the true signal of the measured tissue components, in order to minimize the adverse effects of jitter, a refractive index matching material can be filled between the photosensitive surface and the measurement area to improve the stability and efficiency of the photosensitive surface in receiving the emitted light.

[0560] To illustrate this, let's take the trembling caused by the pulse as an example. The pulse can be reflected in the state of the blood vessels. Figure 37The illustration schematically shows a photosensitive surface receiving outgoing light without being filled with a refractive index matching material, according to an embodiment of the present disclosure. Figure 38 In the diagram, vascular state 1 represents vasoconstriction, vascular state 2 represents vasodilation, skin state 1 represents the skin state corresponding to vascular state 1, and skin state 2 represents the skin state corresponding to vascular state 2. From... Figure 39 It can be seen that shaking causes instability on the skin surface of the measurement area, which in turn causes changes in the emission angle of the emitted light.

[0561] Figure 38 The illustration schematically shows a photosensitive surface receiving emitted light in the presence of a refractive index matching material, according to an embodiment of the present disclosure.

[0562] Figure 39 The illustration schematically shows another example of a photosensitive surface receiving outgoing light when filled with a refractive index matching material, according to an embodiment of the present disclosure.

[0563] from Figure 40 and Figure 40 It can be seen that filling the space between the photosensitive surface and the measurement area with a refractive index matching material can improve the stability and efficiency of the photosensitive surface in receiving outgoing light.

[0564] According to embodiments of this disclosure, the surfaces of S out of the M photosensitive surfaces are respectively provided with filters for filtering out incident light of a first preset wavelength and extracting a second preset wavelength, where 1 ≤ S ≤ M. The filters include long-pass filters and band-pass filters. Alternatively, the filters include band-stop filters and band-pass filters.

[0565] According to embodiments of this disclosure, to obtain the second preset wavelength, a filter can be disposed on the surface of the photosensitive surface. The filter may include a long-pass filter and a band-pass filter. The long-pass filter is used to filter out as much of the first preset wavelength (i.e., incident light), and the band-pass filter is used to allow the second preset wavelength (i.e., Raman scattered light) to pass through. The two filters work together to filter out the first preset wavelength and measure the second preset wavelength. Alternatively, the filter may also include a band-stop filter and a band-pass filter. The band-stop filter is used to filter out as much of the first preset wavelength as possible, and the band-pass filter is used to allow the second preset wavelength to pass through. The two filters work together to filter out the first preset wavelength and measure the second preset wavelength.

[0566] Any one or more of the modules or units according to embodiments of this disclosure, or at least part of the functions of any one or more of them, can be implemented in one module. Any one or more of the modules or units according to embodiments of this disclosure can be implemented by dividing them into multiple modules. Any one or more of the modules or units according to embodiments of this disclosure can be at least partially implemented as hardware circuits, such as Field Programmable Gate Arrays (FPGAs), Programmable Logic Arrays (PLAs), Systems-on-Chip, Systems-on-Substrate, Systems-on-Package, Application-Specific Integrated Circuits (ASICs), or can be implemented by hardware or firmware in any other reasonable manner by integrating or packaging circuits, or implemented by any one of software, hardware, and firmware, or by a suitable combination of any of these. Alternatively, one or more of the modules or units according to embodiments of this disclosure can be at least partially implemented as computer program modules, which can perform corresponding functions when the computer program module is run.

[0567] For example, any number of the acquisition module and processing module can be combined into one module / unit, or any one of the modules / units can be split into multiple modules / units. Alternatively, at least part of the functionality of one or more of these modules / units can be combined with at least part of the functionality of other modules / units and implemented in one module / unit. According to embodiments of this disclosure, at least one of the acquisition module and processing module can be at least partially implemented as hardware circuitry, such as a field-programmable gate array (FPGA), a programmable logic array (PLA), a system-on-a-chip, a system-on-a-substrate, a system-on-package, an application-specific integrated circuit (ASIC), or any other reasonable means of integrating or packaging the circuitry, or implemented in software, hardware, or firmware, or in any suitable combination of any of these three implementation methods. Alternatively, at least one of the acquisition module and processing module can be at least partially implemented as a computer program module, which, when run, can perform corresponding functions.

[0568] It should be noted that the tissue composition measuring device in the embodiments of this disclosure corresponds to the tissue composition measuring method in the embodiments of this disclosure. For a detailed description of the tissue composition measuring device, please refer to the tissue composition measuring method section, which will not be repeated here.

[0569] Figure 40 A schematic diagram of a wearable device according to an embodiment of the present disclosure is shown. Figure 41The wearable device 4000 shown is merely an example and should not be construed as limiting the functionality and scope of use of the embodiments disclosed herein.

[0570] like Figure 41 As shown, the wearable device 4000 includes a tissue composition measurement device 1600 based on Raman scattering.

[0571] According to the technical solution of this disclosure, by irradiating the measurement area with incident light of a first preset wavelength, the incident light of the first preset wavelength passes through the measurement area and exits from the exit position to form at least one beam of Raman scattered light of a second preset wavelength. The wavelength difference between the first preset wavelength and the second preset wavelength is determined according to a preset Raman shift. The Raman intensity corresponding to each beam of Raman scattered light is acquired by the measurement probe. The tissue component measurement device equipped with the measurement probe has a signal-to-noise ratio level that satisfies the requirement to distinguish the expected changes in the concentration of tissue components. The concentration of the measured tissue component is determined based on at least one Raman intensity corresponding to the second preset wavelength. Since the tissue component measurement device equipped with the measurement probe has a signal-to-noise ratio level that can distinguish the expected changes in the concentration of tissue components, the ability to sense the expected changes in the concentration of tissue components is realized, thereby increasing the possibility of obtaining the actual measured tissue component signal.

[0572] like Figure 42 As shown, according to an embodiment of this disclosure, the wearable device 4000 further includes a latching part 4010 and a body 4020. The latching part 4010 and the body 4020 are used to cooperate in fixing the Raman scattering-based tissue composition measuring device 1600.

[0573] According to embodiments of this disclosure, Figure 42 The diagram illustrates an assembly process for a wearable device according to an embodiment of the present disclosure.

[0574] According to embodiments of this disclosure, the mass of the wearable device 4000 is less than or equal to a mass threshold, so that the movement pattern of the wearable device 4000 is consistent with the skin tremor pattern at the measurement area.

[0575] According to embodiments of this disclosure, to improve the likelihood of acquiring accurate signals of the measured tissue components, the wearable device 4000 can be made lighter. This allows the wearable device 4000 to follow skin vibrations in the measurement area when positioned corresponding to the measurement area. In other words, the movement pattern of the wearable device 4000 can be consistent with the skin vibration pattern in the measurement area. Consequently, the average optical path of the emitted light received by the measuring probe 1640 remains within a preset optical path range during skin vibrations. The reason why the average optical path of the emitted light received by the measuring probe 1640 can remain within a preset optical path range during skin vibrations in the measurement area is that if the wearable device 4000 can follow skin vibrations in the measurement area, the relative position of the measuring probe 1640 in the measurement area remains unchanged or substantially unchanged. Therefore, the measuring probe 1640 can receive emitted light from a fixed emission position, where the fixed emission position refers to an emission position whose relative position to the measurement area remains unchanged or substantially unchanged. Meanwhile, during the skin shaking process in the measurement area, the relative position of the incident light on the measurement area can remain unchanged or remain basically unchanged. Therefore, when the incident position of the incident light and the exit position of the exit light are determined, the average optical path of the exit light can be kept as constant as possible.

[0576] For example, Figure 43 This schematically illustrates an embodiment of the present disclosure whereby the average optical path of the emitted light received by the measuring probe remains within a preset optical path range during skin tremors, while maintaining consistency between the wearable device and the skin's tremors. During skin tremors, the measuring probe 1640 ( Figure 43 (Not shown) It can stably receive the incident light from the incident position A in the measurement area and the emitted light from the exit position B in the measurement area. The movement amplitude of the skin is represented by ζ1, and the movement amplitude of the measuring probe 1640 is represented by ζ2, ζ1=ζ2.

[0577] According to embodiments of this disclosure, the wearable device 4000 causes the movement of the skin at the measurement area to be less than or equal to a movement amplitude threshold.

[0578] According to embodiments of this disclosure, in order to improve the possibility of obtaining accurate signals of the components of the measured tissue, the wearable device 4000 can be made to have a larger mass. When the wearable device 4000 is positioned at a location corresponding to the measurement area, it can suppress skin vibrations at the measurement area, meaning the movement amplitude of the skin at the measurement area is less than or equal to a movement amplitude threshold. This ensures that the average optical path of the emitted light received by the measurement probe 1640 remains within a preset optical path range during skin vibrations. The reason why the average optical path of the emitted light received by the measurement probe 1640 can remain within a preset optical path range during skin vibrations at the measurement area is that if the wearable device 4000 can suppress skin vibrations at the measurement area, the relative position of the measurement probe 1640 on the measurement area can be kept as constant or substantially constant as possible. Therefore, the measurement probe 1640 can receive emitted light emitted from a fixed emission position. Meanwhile, during the skin shaking process in the measurement area, the relative position of the incident light on the measurement area can remain unchanged or remain basically unchanged. Therefore, when the incident position of the incident light and the exit position of the exit light are determined, the average optical path of the exit light can be kept as constant as possible.

[0579] For example, ​ The illustration schematically shows a method according to an embodiment of the present disclosure in which the average optical path of the emitted light received by the measuring probe remains within a preset optical path range during skin shaking when the movement amplitude of the skin in the measurement area is less than or equal to a movement amplitude threshold. ​ The skin movement in the measurement area was close to zero.

[0580] According to embodiments of this disclosure, a detailed description of the tissue composition measuring apparatus can be found in the corresponding sections above, and will not be repeated here. Furthermore, the tissue composition measuring apparatus includes a processor that can perform various appropriate actions and processes based on a program stored in read-only memory (ROM) or a program loaded from storage into random access memory (RAM). The processor may include, for example, a general-purpose microprocessor (e.g., a CPU), an instruction set processor and / or an associated chipset and / or a special-purpose microprocessor (e.g., an application-specific integrated circuit (ASIC)), etc. Processing may also include onboard memory for caching purposes. The processor may include a single processing unit or multiple processing units for performing different actions of the method flow according to embodiments of this disclosure.

[0581] The RAM stores various programs and data required for the operation of the tissue composition measuring device. The processor, ROM, and RAM are interconnected via a bus. The processor executes various operations of the method flow according to embodiments of this disclosure by executing programs in the ROM and / or RAM. It should be noted that the programs may also be stored in one or more memories other than ROM and RAM. The process may also execute various operations of the method flow according to embodiments of this disclosure by executing programs stored in said one or more memories.

[0582] According to embodiments of this disclosure, the wearable device may further include an input / output (I / O) interface, which is also connected to a bus. The wearable device may also include one or more of the following components connected to the I / O interface: an input section including a keyboard, mouse, etc.; an output section including a cathode ray tube (CRT), liquid crystal display (LCD), etc., and a speaker, etc.; a storage section including a hard disk, etc.; and a communication section including a network interface card such as a LAN card, modem, etc. The communication section performs communication processing via a network such as the Internet. A drive is also connected to the I / O interface as needed. Removable media, such as a disk, optical disk, magneto-optical disk, semiconductor memory, etc., are installed on the drive as needed so that computer programs read from them can be installed into the storage section as needed.

[0583] This disclosure also provides a computer-readable storage medium, which may be included in the device / apparatus / system described in the above embodiments; or it may exist independently and not assembled into the device / apparatus / system. The computer-readable storage medium carries one or more programs that, when executed, implement the method according to the embodiments of this disclosure.

[0584] According to embodiments of this disclosure, the computer-readable storage medium can be a non-volatile computer-readable storage medium. Examples include, but are not limited to: portable computer hard disks, hard disks, random access memory (RAM), read-only memory (ROM), erasable programmable read-only memory (EPROM) or flash memory, portable compact disk read-only memory (CD-ROM), optical storage devices, magnetic storage devices, or any suitable combination thereof. In this disclosure, the computer-readable storage medium can be any tangible medium that contains or stores a program that...

Claims

1. A method for measuring tissue composition based on Raman spectroscopy, comprising: The measurement area is illuminated by incident light of a first preset wavelength. After passing through the measurement area, the incident light of the first preset wavelength is emitted from the emission position to form at least one beam of Raman scattered light of a second preset wavelength. The wavelength difference between the first preset wavelength and the second preset wavelength is determined according to a preset Raman shift. The Raman intensity corresponding to each beam of Raman scattered light is acquired by a measuring probe, wherein the tissue composition measuring device equipped with the measuring probe has a signal-to-noise ratio level that satisfies the requirement to resolve expected changes in tissue component concentration. The measuring probe includes M photosensitive surfaces, each capable of acquiring the light intensity value of Raman scattered light emitted from an emission position within a preset anti-shake range corresponding to the photosensitive surface. The ratio of the area to the perimeter of the photosensitive surface is greater than or equal to a ratio threshold, where the perimeter represents the edge portion of the photosensitive surface, and the area represents the non-edge portion of the photosensitive surface. The concentration of the tissue component being tested is determined based on at least one Raman intensity corresponding to the second preset wavelength.

2. The method according to claim 1, wherein, The acquisition of the Raman intensity corresponding to each beam of Raman scattered light collected by the measuring probe includes: With fluorescence interference shielded, the Raman intensity corresponding to each beam of Raman scattered light is acquired by the measurement probe.

3. The method according to claim 2, further comprising: Fluorescence interference is shielded using a time-gating method.

4. The method according to claim 1, wherein, The same incident light beam is irradiated to different incident positions by a beam splitting method.

5. The method according to claim 1, wherein, The acquisition of the Raman intensity corresponding to each beam of Raman scattered light collected by the measuring probe, wherein the tissue composition measuring device equipped with the measuring probe has a signal-to-noise ratio level that satisfies the requirement to resolve expected changes in tissue component concentration, includes: The light intensity values ​​corresponding to each beam of Raman scattered light collected by the M photosensitive surfaces are obtained to obtain T Raman intensities. Each Raman intensity is obtained by processing the light intensity values ​​of Raman scattered light collected by one or more photosensitive surfaces. The total area of ​​the same type of photosensitive surfaces is greater than or equal to an area threshold and the area of ​​each photosensitive surface in the same type of photosensitive surface is continuous. The same type of photosensitive surfaces includes one or more photosensitive surfaces. The same type of photosensitive surfaces are used to output a Raman intensity, 1≤T≤M, so that the tissue composition measuring device has a signal-to-noise ratio level that satisfies the requirement to distinguish the expected changes in tissue composition concentration.

6. The method according to claim 1, wherein, The proportion of the average optical path of the Raman scattered light received by each of the photosensitive surfaces in the target tissue layer to the total optical path is greater than or equal to a proportion threshold, wherein the total optical path is the total distance the Raman scattered light travels in the measurement area.

7. The method according to claim 1, further comprising: The total area of ​​similar photosensitive surfaces is determined based on the tissue structure characteristics within the measurement area.

8. The method according to claim 1, wherein, The ratio threshold is greater than or equal to 0.04 mm.

9. The method according to claim 1 or 6, wherein, The photosensitive surface may be in contact with or not in contact with the surface of the measurement area.

10. The method according to claim 9, wherein, The distance between the photosensitive surface and the surface of the measurement area is less than or equal to a first distance threshold, and the efficiency of the photosensitive surface in receiving Raman scattered light is greater than or equal to an efficiency threshold.

11. The method according to claim 1 or 6, wherein, Each of the photosensitive surfaces includes an annular photosensitive surface or a non-annular photosensitive surface, and the different photosensitive surfaces may have the same or different shapes.

12. The method according to claim 11, wherein, The non-annular photosensitive surface includes a fan-shaped photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface.

13. The method according to claim 12, wherein, The polygonal photosensitive surface includes a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

14. The method according to claim 11, wherein, The same type of photosensitive surface includes the annular photosensitive surface or the non-annular photosensitive surface.

15. The method according to claim 14, wherein, The same type of photosensitive surface is the annular photosensitive surface, including: In the case where the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent annular photosensitive surface; When the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is an annular photosensitive surface formed by combining multiple photosensitive surfaces; The same type of photosensitive surface refers to the non-annular photosensitive surface, including: In the case where the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-annular photosensitive surface; In the case where the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed by combining multiple photosensitive surfaces.

16. The method according to claim 15, wherein, When it is determined that the distance between the photosensitive surface of the same type and the target part is greater than or equal to the second distance threshold, the photosensitive surface of the same type includes annular photosensitive surface, fan-shaped photosensitive surface, fan-shaped photosensitive surface, circular photosensitive surface or square photosensitive surface.

17. The method according to claim 15, wherein, When it is determined that the distance between the photosensitive surface of the same type and the target part is less than or equal to a third distance threshold, the shape of the photosensitive surface of the same type is determined according to the jitter distribution of the Raman scattered light.

18. The method according to claim 17, wherein, The jitter distribution of the Raman scattered light is decomposed into a jitter distribution along a first direction and a jitter distribution along a second direction, wherein the first direction and the second direction are perpendicular to each other. The ratio of the length of the same type of photosensitive surface along the first direction to the length of the same type of photosensitive surface along the second direction is determined based on the ratio of the jitter amplitude of the Raman scattered light along the first direction to the jitter amplitude of the Raman scattered light along the second direction, wherein the jitter amplitude of the Raman scattered light along the first direction is the largest.

19. The method according to claim 18, wherein, The same type of photosensitive surface includes a rectangular photosensitive surface or an elliptical photosensitive surface. The ratio of the length to the width of the rectangular photosensitive surface is determined based on the ratio of the dithering amplitude of the Raman scattered light along the first direction to the dithering amplitude of the Raman scattered light along the second direction. The ratio of the major axis to the minor axis of the elliptical photosensitive surface is determined based on the ratio of the dithering amplitude of the Raman scattered light along the first direction to the dithering amplitude of the Raman scattered light along the second direction.

20. The method according to claim 1 or 2, wherein, Determining the concentration of the tested tissue component based on at least one Raman intensity corresponding to the second preset wavelength includes: The concentration of the tested tissue component is determined by processing at least one Raman intensity corresponding to the second preset wavelength using an interference suppression method.

21. The method according to claim 20, wherein, The method of processing at least one Raman intensity corresponding to the second preset wavelength based on interference suppression to determine the concentration of the tested tissue component includes: The first Raman intensity and the second Raman intensity are determined from at least two Raman intensities corresponding to the second preset wavelength; The first Raman intensity and the second Raman intensity corresponding to the second preset wavelength are differentially processed to obtain a differential signal; and The concentration of the tested tissue component is determined based on the differential signal corresponding to the second preset wavelength.

22. The method according to claim 21, wherein, The step of differentially processing the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength to obtain a differential signal includes: The differential signal is obtained by processing the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength using a differential circuit.

23. The method according to claim 21, wherein, The step of differentially processing the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength to obtain a differential signal includes: The differential signal is obtained by processing the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength using a differential algorithm.

24. The method according to claim 23, wherein, The step of processing the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength using a differential algorithm to obtain the differential signal includes: The differential signal is obtained by performing a direct differential operation on the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength.

25. The method according to claim 23, wherein, The step of processing the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength using a differential algorithm to obtain the differential signal includes: The first and second Raman scattered light intensities corresponding to the second preset wavelength are logarithmically divided to obtain the first logarithmic light intensity and the second logarithmic light intensity; and The differential signal is obtained by directly differentially calculating the first logarithmic light intensity and the second logarithmic light intensity corresponding to the second preset wavelength.

26. The method according to claim 21, wherein, The first Raman intensity and the second Raman intensity are obtained by the same or different photosensitive surfaces of the same type at different times. The first Raman intensity is the light intensity during the contraction period, and the second Raman intensity is the light intensity during the relaxation period. The photosensitive surfaces of the same type include one or more of the photosensitive surfaces, and the photosensitive surfaces of the same type are used to output a Raman intensity.

27. The method according to claim 21, wherein, The first Raman intensity corresponding to the second preset wavelength is obtained by a first similar photosensitive surface corresponding to the second preset wavelength, and the second Raman intensity corresponding to the second preset wavelength is obtained by a second similar photosensitive surface corresponding to the second preset wavelength. The first similar photosensitive surface includes one or more of the photosensitive surfaces, and the second similar photosensitive surface includes one or more of the photosensitive surfaces.

28. The method according to claim 27, wherein, The first and second similar photosensitive surfaces are the same type of photosensitive surfaces, and the Raman scattered light received by the first and second similar photosensitive surfaces is obtained by the incident light being incident from different incident positions and transmitted.

29. The method according to claim 27, wherein, The first and second similar photosensitive surfaces are different similar photosensitive surfaces.

30. The method according to claim 27, wherein, The average optical path of the Raman scattered light received at different photosensitive positions of each photosensitive surface in the first type of photosensitive surface belongs to the first average optical path range, wherein the first average optical path range is determined based on the first average optical path value, which is the average value calculated based on the average optical path of the Raman scattered light received at each photosensitive position of the first type of photosensitive surface. The average optical path length of the Raman scattered light received at different photosensitive positions of each photosensitive surface in the second type of photosensitive surface belongs to the second average optical path length range, wherein the second average optical path length range is determined based on the second average optical path length, which is the average value calculated based on the average optical path length of the Raman scattered light received at each photosensitive position of the second type of photosensitive surface.

31. The method according to claim 30, wherein, The absolute value of the difference between the first optical path average value and the second optical path average value falls within the range of the first optical path difference.

32. The method according to claim 31, wherein, The first average optical path range is less than or equal to the first optical path difference range, and the second average optical path range is less than or equal to the first optical path difference range.

33. The method according to claim 31, wherein, The first optical path difference range is determined based on the optimal differential optical path corresponding to the second preset wavelength.

34. The method according to claim 27, wherein, In the first type of photosensitive surface corresponding to the second preset wavelength, the source-detection distance of each photosensitive surface from the center of the incident light is within a preset source-detection distance range corresponding to the second preset wavelength, wherein the preset source-detection distance range is determined based on the source-detection distance of the floating reference position corresponding to the second preset wavelength from the center of the incident light.

35. The method according to claim 1 or 2, wherein, Determining the concentration of the tested tissue component based on at least one Raman intensity corresponding to the second preset wavelength includes: Determine a third Raman intensity from at least one Raman intensity corresponding to the second preset wavelength; and The concentration of the tested tissue component is determined based on the third Raman intensity corresponding to the second preset wavelength.

36. The method according to claim 35, wherein, The third Raman intensity corresponding to the second preset wavelength is obtained by a photosensitive surface of the same type corresponding to the second preset wavelength. The difference between the average optical path of the Raman scattered light received at different photosensitive positions of each photosensitive surface of the same type and the optimal optical path corresponding to the second preset wavelength belongs to the second optical path difference range.

37. The method according to claim 5, wherein, Each of the Raman intensities is obtained by processing the Raman scattered light intensity values ​​collected by one or more of the photosensitive surfaces, including: The one or more photosensitive surfaces are used in combination to output one of the Raman intensities; or When each of the one or more photosensitive surfaces is used individually, the Raman intensity is calculated by analyzing the light intensity values ​​of the Raman scattered light collected by each of the photosensitive surfaces.

38. The method according to claim 20, wherein, The measurement area is illuminated by incident light of a first preset wavelength, including: Under the condition of reproducibility that meets the controllable measurement conditions, the measurement area is illuminated with incident light of the first preset wavelength.

39. The method of claim 38, further comprising: Determine the location features; Based on the positioning features, the measurement area is determined, wherein the measurement area is a reproducible area that satisfies controllable measurement conditions; as well as Set the measuring probe at the position corresponding to the measuring area.

40. The method according to claim 39, wherein, The positioning features include first posture positioning features and region positioning features; Determining the measurement area based on the positioning features includes: Based on the first posture positioning feature, the current measurement posture of the object under test is adjusted to the target measurement posture, wherein the target measurement posture is a reproducible measurement posture that satisfies the controllable measurement conditions; and When the current measurement posture is the target measurement posture, the measurement area is determined based on the area positioning features.

41. The method according to claim 40, wherein, Setting the measuring probe at a position corresponding to the measuring area includes: The measuring probe is positioned at a location corresponding to the measuring area by means of a fixing part, wherein the fixing part and the measuring probe are integral, partially separate, or completely separate.

42. The method according to claim 41, wherein, The fixing part includes a fixing seat and a first mating component; The step of setting the measuring probe at a position corresponding to the measuring area via the fixing part includes: The fixing base is positioned at a location corresponding to the measurement area using the first mating component; as well as The measuring probe is mounted on the fixed base.

43. The method according to claim 42, wherein, The skin condition at the measurement area meets a first preset condition during the process of setting the fixing seat in the position corresponding to the measurement area by the first mating member.

44. The method according to claim 42, wherein, The skin condition at the measurement area meets the second preset condition during the process of setting the measurement probe on the fixed base.

45. The method according to claim 42, wherein, The measuring probe does not move within the fixed base.

46. ​​The method according to claim 41, wherein, The fixing part includes a second mating component; The step of setting the measuring probe at a position corresponding to the measuring area via the fixing part includes: The measuring probe is positioned at a location corresponding to the measuring area using the second mating component.

47. The method according to claim 46, wherein, The skin condition at the measurement area meets a third preset condition during the process of setting the measurement probe to the position corresponding to the measurement area using the second fitting component.

48. The method according to claim 41, wherein, Determining the measurement area based on the regional positioning features includes: Obtain the first projection feature; If it is determined that the area positioning feature does not match the first projection feature, adjust the position of the measuring probe and / or the fixing part until the area positioning feature matches the first projection feature; and If the location feature of the region matches the first projection feature, the region corresponding to the measuring probe and / or the fixing part is determined as the measuring region.

49. The method according to claim 41, wherein, Determining the measurement area based on the regional positioning features includes: Acquire the first target image; Obtain a first template image, wherein the first template image includes the region localization features; If it is determined that the first target image does not match the first template image, the position of the measuring probe and / or the fixing part is adjusted to obtain a new first target image until the new first target image matches the first template image; and If it is determined that the first target image matches the first template image, the area corresponding to the measuring probe and / or the fixing part is determined as the measuring area.

50. The method according to claim 41, wherein, Determining the measurement area based on the regional positioning features includes: Acquire a second target image, wherein the second target image includes the region localization features; If the location of the regional positioning feature in the second target image is determined to be not at the first preset location, the position of the measuring probe and / or the fixing part is adjusted to obtain a new second target image until the location of the regional positioning feature in the new second image is at the first preset location; and If the location of the regional positioning feature in the new second target image is determined to be the first preset location, the region corresponding to the measuring probe and / or the fixing part is determined as the measuring region.

51. The method according to claim 41, wherein, The step of adjusting the current measurement posture of the object under test to the target measurement posture based on the first posture positioning feature includes: Obtain the second projection feature; If it is determined that the first posture positioning feature and the second projection feature do not match, the current measurement posture is adjusted until the first posture positioning feature and the second projection feature match; and If the first pose localization feature is determined to match the second projection feature, the current measurement pose is determined to be the target measurement pose.

52. The method according to claim 41, wherein, The step of adjusting the current measurement posture of the object under test to the target measurement posture based on the first posture positioning feature includes: Acquire the third target image; Obtain a second template image, wherein the second template image includes the first pose localization features; If it is determined that the third target image does not match the second template image, the current measurement pose is adjusted to obtain a new third target image until the new third target image matches the second template image; and If the new third target image is determined to match the second template image, the current measurement pose is determined to be the target measurement pose.

53. The method according to claim 41, wherein, The step of adjusting the current measurement posture of the object under test to the target measurement posture based on the first posture positioning feature includes: Acquire a fourth target image, wherein the fourth target image includes the first pose localization features; If it is determined that the position of the first pose localization feature in the fourth target image is not at the second preset position, the current measurement pose is adjusted to obtain a new fourth target image until the position of the first pose localization feature in the new fourth target image is at the second preset position; and If the position of the first pose localization feature in the new fourth target image is determined to be the second preset position, the current measurement pose is determined to be the target measurement pose.

54. The method of claim 41, further comprising: If the measuring probe is positioned at a location corresponding to the measuring area, then if it is determined that the current measuring posture is not the target measuring posture, a second posture positioning feature is determined. as well as Based on the second posture positioning features, the current measurement posture is adjusted to the target measurement posture.

55. The method according to claim 54, wherein, The step of adjusting the current measurement posture to the target measurement posture based on the second posture positioning features includes: Obtain the third projection feature; If it is determined that the second pose positioning feature does not match the third projection feature, the current measurement pose is adjusted until the second pose positioning feature matches the third projection feature; and If the second pose localization feature is determined to match the third projection feature, the current measurement pose is determined to be the target measurement pose.

56. The method according to claim 54, wherein, The step of adjusting the current measurement posture to the target measurement posture based on the second posture positioning features includes: Acquire the image of the fifth target; Obtain a third template image, wherein the third template image includes the second pose localization features; If it is determined that the fifth target image does not match the third template image, the current measurement posture is adjusted to obtain a new fifth target image until the new fifth target image matches the third template image; and If the new fifth target image is determined to match the third template image, the current measurement pose is determined to be the target measurement pose.

57. The method according to claim 54, wherein, The step of adjusting the current measurement posture to the target measurement posture based on the second posture positioning features includes: Acquire a sixth target image, wherein the sixth target image includes the second pose localization features; If it is determined that the position of the second pose localization feature in the sixth target image is not at the third preset position, the current measurement pose is adjusted to obtain a new sixth target image until the position of the second pose localization feature in the new sixth target image is at the third preset position; and If the position of the second pose localization feature in the new sixth target image is determined to be the third preset position, the current measurement pose is determined to be the target measurement pose.

58. The method of claim 54, further comprising: Generate prompt information, wherein the prompt information is used to indicate that the measurement posture positioning and / or measurement area positioning is completed, and the form of the prompt information includes at least one of image, voice or vibration.

59. The method of claim 42, further comprising: When it is determined that the fixing base is set at a position corresponding to the measurement area and the measurement probe is not set at the fixing part, the measurement probe is set at the fixing base; If it is determined that the fixing base is not set in the position corresponding to the measurement area, the fixing base is set in the position corresponding to the measurement area by the first mating member, and the measuring probe is set in the fixing base.

60. The method of claim 46, further comprising: If it is determined that the measuring probe is not positioned in the location corresponding to the measuring area, the measuring probe is positioned in the location corresponding to the measuring area using the second mating component.

61. The method according to claim 5, wherein, The photosensitive surface is obtained by setting a mask on the initial photosensitive surface, and the transmittance of the mask is less than or equal to the transmittance threshold.

62. The method according to claim 61, wherein, The shape of the mask is determined based on the jitter distribution of the Raman scattered light.

63. The method according to claim 1 or 2, wherein, The intensity distribution of the light spot illuminating the measurement area by the incident light is uniform.

64. The method according to claim 1 or 2, wherein, The area of ​​the light spot that the incident light illuminates in the measurement area is greater than or equal to the light spot area threshold.

65. A tissue composition measuring device based on Raman scattering, comprising: A light source module is used to illuminate a measurement area with incident light of a first preset wavelength. After passing through the measurement area, the incident light of the first preset wavelength is emitted from the emission position to form at least one beam of Raman scattered light of a second preset wavelength. The wavelength difference between the first preset wavelength and the second preset wavelength is determined according to a preset Raman shift. A data acquisition module is used to acquire the Raman intensity corresponding to each beam of Raman scattered light acquired by a measurement probe. The tissue composition measurement device equipped with the measurement probe has a signal-to-noise ratio level sufficient to resolve expected changes in tissue component concentration. The measurement probe includes M photosensitive surfaces, each capable of acquiring the light intensity value of Raman scattered light emitted from an emission position within a preset anti-shake range corresponding to the photosensitive surface. The ratio of the area to the perimeter of the photosensitive surface is greater than or equal to a ratio threshold, where the perimeter represents the edge portion of the photosensitive surface, and the area represents the non-edge portion of the photosensitive surface. The processing module is used to determine the concentration of the component of the tissue being tested based on at least one Raman intensity corresponding to the second preset wavelength.

66. The apparatus of claim 65 further includes a time-gating module for shielding fluorescence interference.

67. The apparatus of claim 65, wherein the same beam of incident light is directed to different incident positions by a beam splitting method.

68. The apparatus according to claim 65, wherein, The acquisition module includes an acquisition unit; The acquisition unit is used to acquire the light intensity value corresponding to each beam of Raman scattered light acquired by the M photosensitive surfaces, and obtain T Raman intensities. Each Raman intensity is obtained by processing the light intensity value of Raman scattered light acquired by one or more photosensitive surfaces. The total area of ​​the same type of photosensitive surfaces is greater than or equal to an area threshold and the area of ​​each photosensitive surface in the same type of photosensitive surface is continuous. The same type of photosensitive surface includes one or more photosensitive surfaces. The same type of photosensitive surface is used to output a Raman intensity, 1≤T≤M, so that the tissue composition measurement device has a signal-to-noise ratio level that satisfies the requirement of resolving expected changes in tissue composition concentration.

69. The apparatus according to claim 65, wherein, The proportion of the average optical path of the Raman scattered light received by each of the photosensitive surfaces in the target tissue layer to the total optical path is greater than or equal to a proportion threshold, wherein the total optical path is the total distance the Raman scattered light travels in the measurement area.

70. The apparatus according to claim 65, wherein, The total area of ​​similar photosensitive surfaces is determined based on the tissue structure characteristics within the measurement area.

71. The apparatus according to claim 65, wherein, The ratio threshold is greater than or equal to 0.04 mm.

72. The apparatus according to claim 65 or 69, wherein, The photosensitive surface may be in contact with or not in contact with the surface of the measurement area.

73. The apparatus according to claim 72, wherein, The distance between the photosensitive surface and the surface of the measurement area is less than or equal to a first distance threshold, and the efficiency of the photosensitive surface in receiving Raman scattered light is greater than or equal to an efficiency threshold.

74. The apparatus according to claim 65 or 69, wherein, Each of the photosensitive surfaces includes an annular photosensitive surface or a non-annular photosensitive surface, and the different photosensitive surfaces may have the same or different shapes.

75. The apparatus according to claim 74, wherein, The non-annular photosensitive surface includes a fan-shaped photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface.

76. The apparatus according to claim 75, wherein, The polygonal photosensitive surface includes a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

77. The apparatus according to claim 74, wherein, The same type of photosensitive surface includes the annular photosensitive surface or the non-annular photosensitive surface.

78. The apparatus according to claim 77, wherein, The same type of photosensitive surface is the annular photosensitive surface, including: In the case where the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent annular photosensitive surface; When the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is an annular photosensitive surface formed by combining multiple photosensitive surfaces; The same type of photosensitive surface refers to the non-annular photosensitive surface, including: In the case where the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-annular photosensitive surface; In the case where the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed by combining multiple photosensitive surfaces.

79. The apparatus according to claim 78, wherein, When it is determined that the distance between the photosensitive surface of the same type and the target part is greater than or equal to the second distance threshold, the photosensitive surface of the same type includes annular photosensitive surface, fan-shaped photosensitive surface, fan-shaped photosensitive surface, circular photosensitive surface or square photosensitive surface.

80. The apparatus according to claim 78, wherein, When it is determined that the distance between the photosensitive surface of the same type and the target part is less than or equal to a third distance threshold, the shape of the photosensitive surface of the same type is the area determined according to the jitter distribution of the Raman scattered light.

81. The apparatus according to claim 80, wherein, The jitter distribution of the Raman scattered light is decomposed into a jitter distribution along a first direction and a jitter distribution along a second direction, wherein the first direction and the second direction are perpendicular to each other. The ratio of the length of the same type of photosensitive surface along the first direction to the length of the same type of photosensitive surface along the second direction is determined based on the ratio of the jitter amplitude of the Raman scattered light along the first direction to the jitter amplitude of the Raman scattered light along the second direction, wherein the jitter amplitude of the Raman scattered light along the first direction is the largest.

82. The apparatus according to claim 81, wherein, The same type of photosensitive surface includes a rectangular photosensitive surface or an elliptical photosensitive surface. The ratio of the length to the width of the rectangular photosensitive surface is determined based on the ratio of the dithering amplitude of the Raman scattered light along the first direction to the dithering amplitude of the Raman scattered light along the second direction. The ratio of the major axis to the minor axis of the elliptical photosensitive surface is determined based on the ratio of the dithering amplitude of the Raman scattered light along the first direction to the dithering amplitude of the Raman scattered light along the second direction.

83. The apparatus according to claim 68, wherein, The angle between each part of the photosensitive surface and the direction of the corresponding incident light is greater than or equal to 0° and less than or equal to 360°.

84. The apparatus according to claim 83, wherein, The processing module includes a processing unit; The processing unit is used to process at least one Raman intensity corresponding to the second preset wavelength based on the interference suppression method to determine the concentration of the tested tissue component.

85. The apparatus according to claim 84, wherein, Among the M photosensitive surfaces, there are one or more similar photosensitive surfaces corresponding to the second preset wavelength. The similar photosensitive surfaces are used to collect the first Raman intensity and / or the second Raman intensity corresponding to the second preset wavelength at different times. The first Raman intensity is the light intensity during the contraction period, and the second Raman intensity is the light intensity during the relaxation period. The similar photosensitive surfaces include one or more of the photosensitive surfaces. The processing unit is used to determine the concentration of the tested tissue component based on the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength.

86. The apparatus according to claim 84, wherein, Among the M photosensitive surfaces, there are a first similar photosensitive surface and a second similar photosensitive surface corresponding to the second preset wavelength. The first similar photosensitive surface is used to collect the first Raman intensity corresponding to the second preset wavelength, and the second similar photosensitive surface is used to collect the second Raman intensity corresponding to the second preset wavelength. The first similar photosensitive surface includes one or more of the photosensitive surfaces, and the second similar photosensitive surface includes one or more of the photosensitive surfaces. The processing unit is used to determine the concentration of the tested tissue component based on the first Raman intensity and the second Raman intensity corresponding to the second preset wavelength.

87. The apparatus according to claim 86, wherein, The first and second similar photosensitive surfaces are the same type of photosensitive surfaces, and the Raman scattered light received by the first and second similar photosensitive surfaces is obtained by the incident light being incident from different incident positions and transmitted.

88. The apparatus according to claim 86, wherein, The first and second similar photosensitive surfaces are different similar photosensitive surfaces.

89. The apparatus according to claim 86, wherein, The average optical path of the Raman scattered light received at different photosensitive positions of each photosensitive surface in the first type of photosensitive surface belongs to the first average optical path range, wherein the first average optical path range is determined based on the first average optical path value, which is the average value calculated based on the average optical path of the Raman scattered light received at each photosensitive position of the first type of photosensitive surface. The average optical path length of the Raman scattered light received at different photosensitive positions of each photosensitive surface in the second type of photosensitive surface belongs to the second average optical path length range, wherein the second average optical path length range is determined based on the second average optical path length, which is the average value calculated based on the average optical path length of the Raman scattered light received at each photosensitive position of the second type of photosensitive surface.

90. The apparatus according to claim 89, wherein, The absolute value of the difference between the first optical path average value and the second optical path average value falls within the range of the first optical path difference.

91. The apparatus according to claim 90, wherein, The first average optical path range is less than or equal to the first optical path difference range, and the second average optical path range is less than or equal to the first optical path difference range.

92. The apparatus according to claim 90, wherein, The first optical path difference range is determined based on the optimal differential optical path corresponding to the second preset wavelength.

93. The apparatus according to claim 86, wherein, In the first type of photosensitive surface corresponding to the second preset wavelength, the source-detection distance of each photosensitive surface from the center of the incident light is within a preset source-detection distance range corresponding to the second preset wavelength, wherein the preset source-detection distance range is determined based on the source-detection distance of the floating reference position corresponding to the second preset wavelength from the center of the incident light.

94. The apparatus according to claim 84, wherein, The M photosensitive surfaces include similar photosensitive surfaces corresponding to the second preset wavelength, wherein the similar photosensitive surfaces are used to collect the third Raman intensity corresponding to the second preset wavelength, and the similar photosensitive surfaces include one or more of the photosensitive surfaces; The processing unit is used to determine the concentration of the tested tissue component based on the third Raman intensity corresponding to the second preset wavelength.

95. The apparatus according to claim 94, wherein, The difference between the average optical path length of the Raman scattered light received at different photosensitive positions of each photosensitive surface of the same type and the optimal optical path length corresponding to the second preset wavelength belongs to the second optical path difference range.

96. The apparatus according to claim 68, wherein, Different parts of the same photosensitive surface may be on the same plane or on different planes.

97. The apparatus according to claim 68, wherein, The photosensitive surfaces are arranged in the same plane or different planes, wherein the photosensitive surface set includes multiple photosensitive surfaces.

98. The apparatus according to claim 68, wherein, The anodes of different photosensitive surfaces among the M photosensitive surfaces are not electrically connected to each other, the anodes of some photosensitive surfaces are electrically connected, or the anodes of all photosensitive surfaces are electrically connected.

99. The apparatus according to claim 84, wherein, The light source module includes a light source unit; The light source unit is used to illuminate the measurement area with incident light of the first preset wavelength while satisfying the reproducibility of controllable measurement conditions.

100. The apparatus of claim 99, further comprising: The first determining module is used to determine the location features; The second determining module is used to determine the measurement area based on the positioning features, wherein the measurement area is a reproducible area that satisfies controllable measurement conditions; as well as The setting module is used to set the measuring probe at a position corresponding to the measuring area.

101. The apparatus according to claim 100, wherein, The positioning features include first posture positioning features and region positioning features; The second determining module includes: A first adjustment unit is configured to adjust the current measurement posture of the object under test to a target measurement posture based on the first posture positioning feature, wherein the target measurement posture is a reproducible measurement posture that satisfies the controllable measurement conditions; and The first determining unit is configured to determine the measurement area based on the area positioning features when the current measurement posture is the target measurement posture.

102. The apparatus according to claim 101 further includes a fixing part, the fixing part being used to position the measuring probe at a position corresponding to the measuring area, wherein, The fixing part and the measuring probe can be integrated, partially separate, or completely separate.

103. The apparatus according to claim 102, wherein, The fixing part includes a fixing seat and a first mating component; The first mating component is used to position the fixing base at a position corresponding to the measuring area; and The mounting base is used to fix the measuring probe.

104. The apparatus according to claim 103, wherein, The hardness of the first mating component includes a first hardness and a second hardness, wherein the first hardness is less than the second hardness. The first hardness is the hardness corresponding to the first mating component during the process of fixing the fixing seat, and the second hardness is the hardness corresponding to the first mating component after fixing the fixing seat.

105. The apparatus according to claim 104, wherein, The first mating component includes a first Velcro strap or a first elastic band.

106. The apparatus according to claim 104, wherein, The hardness of the first mating component is greater than or equal to a first hardness threshold and less than or equal to a second hardness threshold.

107. The apparatus of claim 104 further comprises a first magnetic part, all or part of the first mating member being a metal hinge, and the first magnetic part engaging with the first mating member to fix the mounting base.

108. The apparatus according to claim 103, wherein, The surface of the first mating part is provided with holes.

109. The apparatus according to claim 103, wherein, The measuring probe is fixed to the mounting base by at least one of the following methods: The measuring probe is fixed to the mounting base with tape; The measuring probe is fixed to the mounting base by fasteners; The measuring probe is magnetically fixed to the mounting base; The coefficient of friction between the measuring probe and the fixed base is greater than or equal to the coefficient of friction threshold.

110. The apparatus according to claim 102, wherein, The fixing part includes a second mating component; The second mating component is used to position the measuring probe at a location corresponding to the measuring area.

111. The apparatus according to claim 110, wherein, The hardness of the second mating component includes a third hardness and a fourth hardness, wherein the third hardness is less than the fourth hardness. The third hardness is the hardness corresponding to the second mating component during the process of fixing the measuring probe, and the fourth hardness is the hardness corresponding to the second mating component after fixing the measuring probe.

112. The apparatus according to claim 111, wherein, The second mating component includes a second Velcro strap or a second elastic band.

113. The apparatus according to claim 111, wherein, The hardness of the second mating part is greater than or equal to the third hardness threshold and less than or equal to the fourth hardness threshold.

114. The apparatus of claim 111 further comprises a second magnetic part, all or part of the second mating member being a metal hinge, and the second magnetic part cooperating with the second mating member to fix the measuring probe.

115. The apparatus according to claim 110, wherein, The surface of the second mating part is provided with holes.

116. The apparatus according to claim 102, wherein, The first determining unit is configured to: Obtain the first projection feature; If it is determined that the area positioning feature does not match the first projection feature, adjust the position of the measuring probe and / or the fixing part until the area positioning feature matches the first projection feature; and If the location feature of the region matches the first projection feature, the region corresponding to the measuring probe and / or the fixing part is determined as the measuring region.

117. The apparatus according to claim 116 further includes a region positioning unit disposed on the object under test, the measuring probe, the fixing part or other object, the region positioning unit being used to project the first projection feature.

118. The apparatus according to claim 117, wherein, If it is determined that the area positioning part is located on the measuring probe, the area positioning feature is not located on the measuring probe; When it is determined that the area positioning feature is set on the fixed part, the area positioning feature is not set on the fixed part.

119. The apparatus according to claim 117, wherein, The area positioning unit includes a first laser.

120. The apparatus according to claim 102, wherein, The first determining unit is configured to: Acquire the first target image; Obtain a first template image, wherein the first template image includes the region localization features; If it is determined that the first target image does not match the first template image, the position of the measuring probe and / or the fixing part is adjusted to obtain a new first target image until the new first target image matches the first template image; and If it is determined that the first target image matches the first template image, the area corresponding to the measuring probe and / or the fixing part is determined as the measuring area.

121. The apparatus according to claim 120 further includes a first image acquisition unit, the first image acquisition unit being disposed on the object under test, the measuring probe, the fixing part or other object, the first image acquisition unit being used to acquire the first target image.

122. The apparatus according to claim 102, wherein, The first determining unit is configured to: Acquire a second target image, wherein the second target image includes the region localization features; If the location of the regional positioning feature in the second target image is determined to be not at the first preset location, the position of the measuring probe and / or the fixing part is adjusted to obtain a new second target image until the location of the regional positioning feature in the new second image is at the first preset location; and If the location of the regional positioning feature in the new second target image is determined to be the first preset location, the region corresponding to the measuring probe and / or the fixing part is determined as the measuring region.

123. The apparatus according to claim 122 further includes a second image acquisition unit, the second image acquisition unit being disposed on the object under test, the measuring probe, the fixing part or other object, the second image acquisition unit being used to acquire the second target image.

124. The apparatus according to claim 123, wherein, If it is determined that the second image acquisition unit is located on the measuring probe, the area positioning feature is not located on the measuring probe; If it is determined that the second image acquisition unit is located on the fixed part, the area positioning feature is not located on the fixed part.

125. The apparatus according to claim 102, wherein, The first adjustment unit is used for: Obtain the second projection feature; If it is determined that the first posture positioning feature does not match the second projection feature, the current measurement posture is adjusted until the first posture positioning feature matches the second projection feature. as well as If the first pose localization feature is determined to match the second projection feature, the current measurement pose is determined to be the target measurement pose.

126. The apparatus according to claim 125 further includes a first posture positioning unit disposed on the object under test, the measuring probe, the fixing part or other object, the first posture positioning unit being used to project the second projection feature.

127. The apparatus according to claim 126, wherein, In cases where it is determined that the first posture positioning part is disposed on the measuring probe, the first posture positioning feature is not disposed on the measuring probe; In cases where it is determined that the first posture positioning feature is disposed on the fixed part, the first posture positioning feature is not disposed on the fixed part.

128. The apparatus according to claim 126, wherein, The first posture positioning unit includes a second laser.

129. The apparatus according to claim 102, wherein, The first adjustment unit is used for: Acquire the third target image; Obtain a second template image, wherein the second template image includes the first pose localization features; If it is determined that the third target image does not match the second template image, the current measurement pose is adjusted to obtain a new third target image until the new third target image matches the second template image; and If the new third target image is determined to match the second template image, the current measurement pose is determined to be the target measurement pose.

130. The apparatus according to claim 129 further includes a third image acquisition unit disposed on the object under test, the measuring probe, the fixing part or other object, the third image acquisition unit being used to acquire the third target image.

131. The apparatus according to claim 102, wherein, The first adjustment unit is used for: Acquire a fourth target image, wherein the fourth target image includes the first pose localization features; If it is determined that the position of the first pose localization feature in the fourth target image is not at the second preset position, the current measurement pose is adjusted to obtain a new fourth target image until the position of the first pose localization feature in the new fourth target image is at the second preset position; and If the position of the first pose localization feature in the new fourth target image is determined to be the second preset position, the current measurement pose is determined to be the target measurement pose.

132. The apparatus according to claim 131 further includes a fourth image acquisition unit, the fourth image acquisition unit being disposed on the object under test, the measuring probe, the fixing part or other object, the fourth image acquisition unit being used to acquire the fourth target image.

133. The apparatus according to claim 132, wherein, If it is determined that the fourth image acquisition unit is located on the measuring probe, the first posture positioning feature is not located on the measuring probe; When it is determined that the fourth image acquisition unit is disposed on the fixed part, the first posture positioning feature is not disposed on the fixed part.

134. The apparatus of claim 102, further comprising: The third determining module is used to determine the second posture positioning feature if the measuring probe is set at a position corresponding to the measuring area, and the current measuring posture is not the target measuring posture. as well as An adjustment module is used to adjust the current measurement posture to the target measurement posture based on the second posture positioning features.

135. The apparatus according to claim 134, wherein, The adjustment module includes: The first acquisition unit is used to acquire the third projection feature; The second adjustment unit is configured to adjust the current measured posture until the second posture positioning feature matches the third projection feature when it is determined that the second posture positioning feature does not match the third projection feature; and The second determining unit is used to determine the current measurement posture as the target measurement posture when it is determined that the second posture positioning feature matches the third projection feature.

136. The apparatus according to claim 135 further includes a second posture positioning unit disposed on the object under test, the measuring probe, the fixing part or other object, the second posture positioning unit being used to project the third projection feature.

137. The apparatus according to claim 136, wherein, When it is determined that the second posture positioning part is disposed on the measuring probe, the second posture positioning feature is not disposed on the measuring probe and the fixing part; When it is determined that the second posture positioning part is disposed on the fixed part, the second posture positioning feature is not disposed on the measuring probe and the fixed part.

138. The apparatus according to claim 137, wherein, The second posture positioning unit includes a third laser.

139. The apparatus according to claim 134, wherein, The adjustment module includes: The second acquisition unit is used to acquire the fifth target image; The third acquisition unit is used to acquire a third template image, wherein the third template image includes the second pose localization features; The third adjustment unit is configured to adjust the current measurement posture to obtain a new fifth target image when it is determined that the fifth target image does not match the third template image, until the new fifth target image matches the third template image; and The third determining unit is used to determine the current measurement posture as the target measurement posture when it is determined that the new fifth target image matches the third template image.

140. The apparatus according to claim 139 further includes a fifth image acquisition unit, the fifth image acquisition unit being disposed on the object under test, the measuring probe, the fixing part or other object, the fifth image acquisition unit being used to acquire the fifth target image.

141. The apparatus according to claim 134, wherein, The adjustment module includes: The fourth acquisition unit is used to acquire a sixth target image, wherein the sixth target image includes the second pose localization features; The fourth adjustment unit is configured to adjust the current measurement posture to obtain a new sixth target image when the position of the second pose localization feature in the sixth target image is not at the third preset position, until the position of the second pose localization feature in the new sixth target image is at the third preset position; and The fourth determining unit is used to determine the current measurement posture as the target measurement posture when the position of the second posture positioning feature in the new sixth target image is determined to be at the third preset position.

142. The apparatus according to claim 141 further includes a sixth image acquisition unit, the sixth image acquisition unit being disposed on the object under test, the measuring probe, the fixing part or other object, the sixth image acquisition unit being used to acquire the sixth target image.

143. The apparatus according to claim 142, wherein, When it is determined that the second posture positioning part is disposed on the measuring probe, the second posture positioning feature is not disposed on the measuring probe and the fixing part; When it is determined that the second posture positioning part is disposed on the fixed part, the second posture positioning feature is not disposed on the measuring probe and the fixed part.

144. The apparatus of claim 134, further comprising: A prompting module is used to generate prompting information, wherein the prompting information is used to indicate that the measurement posture positioning and / or measurement area positioning is completed, and the form of the prompting information includes at least one of image, voice or vibration.

145. The apparatus according to claim 65, wherein, The photosensitive surface is obtained by setting a mask on the initial photosensitive surface, and the transmittance of the mask is less than or equal to the transmittance threshold.

146. The apparatus according to claim 145, wherein, The shape of the mask is determined based on the jitter distribution of the Raman scattered light.

147. The apparatus according to claim 65, wherein, The measuring probe is equipped with a first sleeve; The first end face of the first sleeve extends beyond the target surface of the measuring probe, wherein the first end face represents the end face close to the measuring area, and the target surface of the measuring probe represents the surface close to the measuring area.

148. The apparatus according to claim 147, wherein, The second end face and / or the inner region of the first sleeve are provided with scattering material, wherein the first end face and the second end face are two opposite end faces, and the inner region includes a portion of the inner region or the entire inner region.

149. The apparatus according to claim 147 or 148, further comprising a second sleeve disposed outside the target region of the first sleeve, wherein, The target area refers to a portion or all of the area of ​​the first sleeve that extends beyond the target surface of the measuring probe.

150. The apparatus according to claim 149, wherein, The second sleeve is provided with the scattering material.

151. The apparatus according to claim 147, wherein, The inner diameter of the first sleeve is greater than or equal to the inner diameter threshold.

152. The apparatus according to claim 147, wherein, The opening on the first end face of the first sleeve is greater than or equal to the opening on the second end face of the first sleeve.

153. The apparatus according to claim 65, wherein, A refractive index matching material is filled between the photosensitive surface and the measurement area.

154. The apparatus according to claim 65, wherein, The surfaces of S of the M photosensitive surfaces are respectively provided with filters for filtering out the first preset wavelength and extracting the second preset wavelength of incident light, where 1≤S≤M; The filter includes a long-pass filter and a band-pass filter; or, The filters include bandstop filters and bandpass filters.

155. A wearable device comprising the tissue composition measuring device according to any one of claims 65 to 154.

156. The wearable device according to claim 155, wherein, The mass of the wearable device is less than or equal to a mass threshold, so that the movement pattern of the wearable device is consistent with the skin shaking pattern in the measurement area.

157. The wearable device according to claim 155, wherein, The wearable device causes the movement of the skin in the measurement area to be less than or equal to a movement threshold.

Images