Tissue composition measurement methods, devices, and wearable devices

Abstract

Embodiments of the present disclosure provide a method, apparatus, and wearable device for measuring tissue components. The method comprises: irradiating a measurement area with incident light of a plurality of preset wavelengths—each of the incident light is emitted from at least one emission position after passing through the measurement area to form at least one emission light, and the emission position of the incident light includes one—; obtaining light intensity values ​​corresponding to each emission light collected by M photosensitive surfaces to obtain T output light intensities—each output light intensity is obtained by processing according to the light intensity value of the emission light collected by one or more photosensitive surfaces, and each of the photosensitive surfaces can collect the light intensity value of the emission light emitted from an emission position within a preset anti-shake range corresponding to the photosensitive surface, and 1 ≤ T ≤ M—; and determining the concentration of a tissue component to be measured according to at least one output light intensity corresponding to a plurality of preset wavelengths.

Description

Technology Field

[0001] The present disclosure relates to the field of optical spectrum measurement technology, and more specifically to a method, apparatus, and wearable device for measuring tissue components. Background Technology

[0002] Human body fluids contain various tissue components, such as blood sugar, lipids, and white blood cells, and the healthy functioning of the body can only be ensured if the concentration of each biological tissue component remains within its corresponding range. However, for some individuals, an imbalance in biological tissue components—specifically, a situation where the concentration falls outside the numerical range—is prone to occurring. Since this leads to disease and threatens health or even life, real-time measurement of tissue components is necessary for such individuals.

[0003] Because optical methods are fast, non-traumatic, and possess characteristics such as multidimensional information, they are generally applied in related technologies to measure tissue composition. When classified according to the measurement principle, optical methods mainly include Raman spectroscopy, polarization, optical coherence tomography, photoacoustic spectroscopy, mid-infrared spectroscopy, and near-infrared spectroscopy. CN105510238A is a prior art related to these tissue composition measurement methods.

[0004] In the process of implementing the concept of the present disclosure, the inventor discovered that there exists a problem in the related technology where the measurement accuracy is not high, at least when applying the related technology.

[0005] In light of this, embodiments of the present disclosure provide a method, apparatus, and wearable device for measuring tissue components.

[0006] One aspect of an embodiment of the present disclosure provides a method for measuring tissue components, the method comprising: irradiating a measurement area with incident light of a plurality of preset wavelengths—each of the incident light is emitted from at least one emission position after passing through the measurement area to form at least one emission light, and the emission position of the incident light includes one—; obtaining light intensity values ​​corresponding to each of the emission light collected by M photosensitive surfaces to obtain T output light intensities—each of the light intensity values ​​is obtained by processing according to the light intensity values ​​of the emission light collected by one or more of the photosensitive surfaces, and each of the photosensitive surfaces can collect light intensity values ​​of the emission light emitted from an emission position within a preset anti-shake range corresponding to the photosensitive surfaces, and 1 ≤ T ≤ M—; and determining the concentration of a tissue component to be measured according to at least one output light intensity corresponding to the plurality of preset wavelengths.

[0007] Another aspect of an embodiment of the present disclosure provides a tissue component measuring device, the device comprising: a light source module for irradiating a measuring area with incident light of a plurality of preset wavelengths, wherein each of the incident light is emitted from at least one emission position after passing through the measuring area to form at least one emission light, and the emission position of the incident light includes one; a collection module comprising M photosensitive surfaces, wherein each of the photosensitive surfaces can collect a light intensity value of an emission light emitted from an emission position within a preset anti-shake range corresponding to the photosensitive surface, and a collection module for obtaining T output light intensities by acquiring a light intensity value corresponding to each of the emission light collected by the M photosensitive surfaces, wherein each of the output light intensities is obtained by processing the light intensity value of the emission light collected by one or a plurality of the photosensitive surfaces, and 1 ≤ T ≤ M; and a processing module for determining the concentration of a tissue component to be measured according to at least one output light intensity corresponding to the plurality of preset wavelengths.

[0008] Another aspect of an embodiment of the present disclosure provides a wearable device comprising a tissue component measuring device as described above. Brief explanation of the drawing

[0009] The above and other purposes, features, and advantages of the present disclosure will become more apparent through the description of embodiments of the present disclosure with reference to the attached drawings. In the drawings, FIG. 1 schematically illustrates a schematic diagram of receiving emitted light with a photosensitive surface of a relatively small area when vibration occurs according to an embodiment of the present disclosure. FIG. 2 schematically illustrates a schematic diagram of receiving emitted light with a photosensitive surface of a relatively large area when vibration occurs according to an embodiment of the present disclosure. FIG. 3 schematically illustrates a flowchart of a method for measuring tissue components according to an embodiment of the present disclosure. FIG. 4 schematically illustrates a schematic diagram of measurement results obtained based on a Monte Carlo simulation method according to an embodiment of the present disclosure. FIG. 5 schematically illustrates a schematic diagram of a difference measurement according to an embodiment of the present disclosure. FIG. 6 schematically illustrates a schematic diagram of a ring-shaped photosensitive surface according to an embodiment of the present disclosure. FIG. 7 schematically illustrates a schematic diagram of a fan-shaped ring photosensitive surface according to an embodiment of the present disclosure. FIG. 8 schematically illustrates a schematic diagram of a circular photosensitive surface according to an embodiment of the present disclosure. FIG. 9 illustrates a square photosensitive surface according to an embodiment of the present disclosure A schematic diagram is shown. FIG. 10 is a schematic diagram showing a photosensitive surface obtained by installing a mask on an initial photosensitive surface according to an embodiment of the present disclosure. FIG. 11 is a schematic block diagram of a tissue component measurement device according to an embodiment of the present disclosure. FIG. 12 is a schematic diagram showing the electrical connection of anodes of different photosensitive surfaces according to an embodiment of the present disclosure. FIG. 13 is a schematic diagram showing a glove-type stereoscopic photosensitive surface according to an embodiment of the present disclosure. FIG. 14 is a schematic diagram showing another glove-type stereoscopic photosensitive surface according to an embodiment of the present disclosure. FIG. 15 is a schematic diagram showing a bracelet-type stereoscopic photosensitive surface according to an embodiment of the present disclosure. FIG. 16 is a schematic diagram showing another bracelet-type stereoscopic photosensitive surface according to an embodiment of the present disclosure. FIG. 17 is a schematic diagram showing a stereoscopic photosensitive surface for arm measurement according to an embodiment of the present disclosure.FIG. 18 schematically illustrates a first sleeve (tweezers) installed on a measurement probe according to an embodiment of the present disclosure. FIG. 19 schematically illustrates a second sleeve installed outside the target area of ​​the first sleeve according to an embodiment of the present disclosure. FIG. 20 schematically illustrates a photosensitive surface receiving emitted light when the refractive index matching material is not filled according to an embodiment of the present disclosure. FIG. 21 schematically illustrates a photosensitive surface receiving emitted light when the refractive index matching material is filled according to an embodiment of the present disclosure. FIG. 22 schematically illustrates another schematic diagram of a photosensitive surface receiving emitted light when the refractive index matching material is filled according to an embodiment of the present disclosure. FIG. 23 schematically illustrates a circular incident light incident on the center and a ring-shaped photosensitive surface receiving it from the outer edge according to an embodiment of the present disclosure. FIG. 24 schematically illustrates a ring-shaped incident light incident on the center and a ring-shaped photosensitive surface receiving it from the outer edge according to an embodiment of the present disclosure. FIG. 25 schematically illustrates a circular incident light incident on the center A schematic diagram is shown in which incident light is incident on the center and received by a fan-shaped ring photosensitive surface at the outer edge. FIG. 26 is a schematic diagram according to an embodiment of the present disclosure in which circular incident light is incident on the center and received by a circular photosensitive surface at the outer edge. FIG. 27 is a schematic diagram according to an embodiment of the present disclosure in which circular incident light is incident on the center and received by two ring-shaped photosensitive surfaces at the outer edge. FIG. 28 is a schematic diagram according to an embodiment of the present disclosure in which circular incident light is incident on the center and received by two fan-shaped ring photosensitive surfaces at the outer edge. FIG. 29 is a schematic diagram according to an embodiment of the present disclosure in which ring-shaped incident light is incident on the outer edge and received by a circular photosensitive surface at the inside. FIG. 30 is a schematic diagram according to an embodiment of the present disclosure in which fan-shaped ring incident light is incident on the outer edge and received by a circular photosensitive surface at the inside.FIG. 31 illustrates an exemplary schematic diagram according to an embodiment of the present disclosure in which circular incident light is incident on the outer edge and received by a circular photosensitive surface inside. FIG. 32 illustrates a schematic diagram according to an embodiment of the present disclosure in which ring-shaped incident light is incident on the outer edge and received by a first set of photosensitive surfaces inside. FIG. 33 illustrates a schematic diagram according to an embodiment of the present disclosure in which ring-shaped incident light is incident on the outer edge and received by a second set of photosensitive surfaces inside. FIG. 34 illustrates a schematic diagram according to an embodiment of the present disclosure in which ring-shaped incident light is incident on the outer edge and received by a third set of photosensitive surfaces including four fan-shaped ring photosensitive surfaces inside. FIG. 35 illustrates a schematic diagram of reception from both sides according to an embodiment of the present disclosure. FIG. 36 illustrates a schematic diagram of a wearable device according to an embodiment of the present disclosure. FIG. 37 illustrates a schematic diagram of an assembly process of a wearable device according to an embodiment of the present disclosure. FIG. 38 illustrates a measurement when the wearable device according to an embodiment of the present disclosure and the skin tremor law are maintained in alignment. FIG. 39 schematically illustrates a schematic diagram in which the average optical path length of the emitted light received by the probe is maintained within a preset optical path length range during skin shaking. Specific details for implementing the invention

[0010] Hereinafter, embodiments of the present disclosure will be described with reference to the attached drawings. However, it should be understood that such description is merely illustrative and is not intended to limit the scope of the present disclosure. In the detailed description below, many specific details are described for convenience of explanation and to provide a comprehensive understanding of the embodiments of the present disclosure. However, it is obvious that one or more embodiments may be implemented without such specific details. Furthermore, to avoid unnecessary confusion regarding the concepts of the present disclosure, descriptions of known configurations and technologies are omitted in the description below.

[0011] The terms used herein are merely for describing specific embodiments and are not intended to limit the present disclosure. Terms such as “comprehensive,” “included,” etc., used herein indicate the presence of the features, steps, operations, and / or parts, but do not exclude the presence or addition of one or more other features, steps, operations, or parts.

[0012] All terms used herein (including technical and scientific terms) have the meaning generally understood by those skilled in the art unless otherwise defined. It should be noted that terms used herein should be interpreted as having a meaning consistent with the context of this specification and should not be interpreted in an idealized or overly inflexible manner.

[0013] Where expressions similar to "at least one of A, B, and C, etc." are used, they should generally be interpreted in the sense of the expression as generally understood by a person skilled in the art (for example, "a system having at least one of A, B, and C" includes, but is not limited to, systems having A alone, systems having B alone, systems having C alone, systems having A and B, systems having A and C, systems having B and C, and / or systems having A, B, and C). Where expressions similar to "at least one of A, B, or C, etc." are used, they should generally be interpreted in the sense of the expression as generally understood by a person skilled in the art (for example, "a system having at least one of A, B, or C" includes, but is not limited to, systems having A alone, systems having B alone, systems having C alone, systems having A and B, systems having A and C, systems having B and C, and / or systems having A, B, and C).

[0014] Research on measuring biological tissue components based on optical methods has already undergone nearly 50 years of development. Although numerous scientific laboratories and companies have poured significant research passion into this field, the absorption of the tissue components themselves is generally relatively weak, and the range of variation in the concentration of these components within the subject itself is also generally small. Consequently, the signals from the tissue components are relatively faint, and external disturbances, such as fluctuations in measurement conditions, can easily obscure these weak signals; to date, no reliable method for measuring biological tissue components has emerged. Therefore, the measurement of biological tissue components is a global challenge that requires urgent resolution. Here, tissue components may include blood glucose, lipids, and leukocytes. The signal from the tissue components represents changes in output light intensity caused by variations in the concentration of the tissue components. Measurement conditions can be understood as conditions that affect the light transmission path within the tissue. Measurement conditions may include both controllable and uncontrollable conditions. Controllable measurement conditions refer to conditions that can be controlled to remain within a preset range of variation (i.e., unchanged or essentially unchanged) through the application of effective control methods during every process of measuring biological tissue components. Here, effective control methods can be implemented by combining hardware design. Uncontrollable measurement conditions refer to conditions that are difficult to predict and possess uncontrollable characteristics. Controllable measurement conditions may include temperature, pressure, measurement area, and measurement posture. Uncontrollable measurement conditions may include physiological background variations and measurement device drift.

[0015] In the process of implementing the concept of the present disclosure, the inventor discovered that the main reasons for the low measurement precision when applying the related technology are as follows.

[0016] The inventor discovered that, assuming other conditions remain unchanged, altering only the intensity distribution of the photobleed irradiated by incident light onto the measurement area yields different measurement results. When comparing measurement results obtained by installing the photosensitive surface close to a blood vessel with those obtained by installing the same photosensitive surface far from the blood vessel under the same conditions, the results obtained by installing it far from the blood vessel are superior to those obtained by installing it close to the blood vessel. Here, the measurement results can be expressed as the relative change in the light intensity values ​​of the emitted light received by the photosensitive surface or the standard deviation of the light intensity values; the smaller the relative change in light intensity values, the better the measurement result, and the smaller the standard deviation of light intensity values, the better the measurement result. When investigating the reasons for the differences in measurement results, it was discovered that changing the intensity distribution of the photobleed irradiated by incident light onto the measurement area can indicate the randomness of the light source irradiation, and the distance from the blood vessel can indicate the strength of the pulse; furthermore, both the randomness of the light source irradiation and the pulse originate from vibration. Therefore, it was found that vibration is one of the causes of low measurement precision.

[0017] Based on research on vibration, it was discovered that vibrations can be classified into internal and external sources depending on their origin. Here, internal sources may include physiological background fluctuations in addition to pulse beats. External sources may include uncertainty in the transmission of incident light itself, in addition to the randomness of light source irradiation. The randomness of light source irradiation can be reflected in the intensity distribution of photobleaching irradiated by the incident light onto the measurement area. Furthermore, it was found that vibrations caused by either internal or external sources can affect the light transmission path within the tissue and, furthermore, influence the intensity distribution of the emitted light in the measurement area.

[0018] To address the problem of low measurement precision caused by vibration, the inventor discovered that the adverse effects of vibration on measurement results can be effectively suppressed by applying a method of collecting light intensity values ​​of emitted light using a photosensitive surface with a relatively large area (i.e., a large-area photosensitive surface). In other words, a large-area photosensitive surface can effectively suppress adverse effects caused by vibration. The so-called "large-area photosensitive surface" can be understood as the area of ​​a photosensitive surface that enables the collection of light intensity values ​​of emitted light from an emission position within a preset vibration-prevention range. The area of ​​the large-area photosensitive surface is continuous, and it is made using a photosensitive material; this differs from a single-point optical fiber reception and a combined reception of multiple single optical fibers. Below, the reason why applying a method of collecting the output light intensity of emitted light using a large-area photosensitive surface can effectively suppress the adverse effects of vibration on measurement results is explained in detail.

[0019] A large-area photosensitive surface can improve the stability of light reception because it increases the proportion of the surface area capable of stably receiving emitted light. Furthermore, this reduces the adverse effects of changes in the intensity distribution of emitted light caused by vibration, thereby improving measurement precision. Here, stability can be expressed as the relative change in the light intensity value of the emitted light received by the photosensitive surface or the standard deviation of the light intensity value; stability is higher when the relative change in light intensity value is small, and stability is higher when the standard deviation of the light intensity value is small.

[0020] For example, the explanation is given using the example of tremors caused by a pulse. A pulse can be reflected through the state of blood vessels. FIG. 1 schematically illustrates a schematic diagram of receiving emitted light with a photosensitive surface of a relatively small area when tremors occur according to an embodiment of the present disclosure. FIG. 2 schematically illustrates a schematic diagram of receiving emitted light with a photosensitive surface of a relatively large area when tremors occur according to an embodiment of the present disclosure. The tremors occurring in FIG. 1 and FIG. 2 are the same. The area of ​​photosensitive surface A in FIG. 1 is smaller than the area of ​​photosensitive surface B in FIG. 2. Both photosensitive surface A and photosensitive surface B are square photosensitive surfaces. In FIG. 1 and FIG. 2, blood vessel state 1 represents a vasoconstriction state, blood vessel state 2 represents a vasodilation state, skin state 1 represents a skin state corresponding to blood vessel state 1, and skin state 2 represents a skin state corresponding to blood vessel state 2. Skin state 1 through skin state 2 reflect tremors.

[0021] In the event that the same vibration occurs, measurement results obtained using photosensitive surfaces of different areas are compared. The measurement results are expressed as the relative change in light intensity values ​​or the standard deviation of light intensity values ​​of the emitted light received by the photosensitive surface within a preset time period. Here, the relative change in light intensity values ​​can be determined by a method in which the difference between the maximum and minimum light intensity values ​​within the preset time period is calculated, the average value of the emitted values ​​within the preset time period is calculated, the ratio of the difference value to the average value is calculated, and that ratio is used as the relative change in light intensity values. The preset time period may be a single pulsation cycle.

[0022] The measurement results also indicated that whether expressed as the relative change in the light intensity value of the emitted light received by the photosensitive surface or as the standard deviation of the light intensity value received by the photosensitive surface, the measurement results obtained with photosensitive surface B were all superior to the measurement results obtained with photosensitive surface A.

[0023] Since the area of ​​photosensitive surface B is larger than the area of ​​photosensitive surface A, it can be clearly demonstrated that a large-area photosensitive surface can improve the stability of receiving emitted light and further reduce the adverse effects of changes in the intensity distribution of emitted light caused by vibration, thereby improving measurement precision.

[0024] Furthermore, since the output light intensity of the emitted light is relatively weak, the change in output light intensity due to changes in the concentration of the tissue components under measurement is also relatively weak. Additionally, because the method of receiving the emitted light applied in related technologies has a relatively low efficiency of the received emitted light, the signal-to-noise ratio of the received output light intensity is relatively low, which further results in low measurement precision. The large-area photosensitive surface of the embodiment of the present disclosure can improve the signal-to-noise ratio of the output light intensity and further improve measurement precision. This is because the large-area photosensitive surface can realize the reception of a wide range of emitted light and improve the efficiency of receiving the emitted light, thereby improving the signal-to-noise ratio of the output light intensity and improving measurement precision.

[0025] It should be noted that relatively high reception stability and efficiency of the emitted light can be achieved when the large-area photosensitive surface described in the embodiments of the present disclosure is located at a relatively small distance from the surface of the measurement area, that is, when it is close to the surface of the measurement area. This cannot be achieved by single-point optical fiber reception or by combined reception of multiple single optical fibers. The reasons for this are, first, limitations imposed by the numerical aperture of the optical fiber; and second, limitations imposed by changes in the state of the optical fiber. Changes in the state of the optical fiber are susceptible to environmental influences, and such changes have a relatively significant impact on the reception stability of the emitted light.

[0026] In addition, it should be noted that a large-area photosensitive surface can generally be applied to improve the signal-to-noise ratio of the output light intensity. In other words, the role generally performed by a large-area photosensitive surface is to improve the signal-to-noise ratio of the output light intensity, which differs from the role primarily performed by the large-area photosensitive surface in the embodiments of the present disclosure, and the role primarily performed by the large-area photosensitive surface in the embodiments of the present disclosure is to effectively suppress flicker.

[0027] The following is explained in combination with specific embodiments.

[0028] FIG. 3 schematically shows a flowchart of a method for measuring tissue components according to an embodiment of the present disclosure.

[0029] As illustrated in FIG. 3, the method includes operations S310 to S330.

[0030] In operation S310, a measurement area is irradiated with incident light of a plurality of preset wavelengths. Each incident light passes through the measurement area and is emitted from at least one exit position to form at least one exit light, and the incident position includes one.

[0031] According to an embodiment of the present disclosure, since different measurement sites have different skin characteristics, such as smoothness, presence or absence of hair, flatness, skin thickness, and softness, an appropriate measurement site must be selected according to the actual situation, for example, the configuration of the measurement probe. The measurement site may include at least one of a finger, palm, arm, forehead, and earlobe. A specific area may be an area within the measurement site.

[0032] According to an embodiment of the present disclosure, a preset wavelength may be a wavelength sensitive to the tissue component being measured. The band to which the preset wavelength belongs may include the ultraviolet band, the visible light band, the near-infrared band, the mid-infrared band, or the far-infrared band. For example, if the tissue component being measured is blood glucose, the preset wavelength may be a wavelength sensitive to blood glucose, specifically 1550 nm or 1609 nm. The incident light may be collimated light or uncollimated light. The incident position of the incident light may include one.

[0033] In operation S320, light intensity values ​​corresponding to each emitted light collected by M photosensitive surfaces are obtained, and T output light intensities are obtained. Here, each output light intensity is obtained by processing according to the light intensity values ​​of the emitted light collected by one or more photosensitive surfaces. Each photosensitive surface can collect light intensity values ​​of emitted light emitted from an emission position within a preset anti-shake range corresponding to the photosensitive surface. Here, am.

[0034] According to an embodiment of the present disclosure, in order to improve measurement precision, each photosensitive surface must be secured to collect light intensity values ​​of the emitted light emitted from an emission position within a preset anti-vibration range corresponding to the photosensitive surface, and this requires the area of ​​the photosensitive surface to be as large as possible. Each photosensitive surface has a corresponding preset anti-vibration range, and the preset anti-vibration ranges of different photosensitive surfaces are the same or different. The following explains, in combination with examples, that the larger the area of ​​the photosensitive surface, the better the effect of suppressing vibration in three aspects. The preset area of ​​photosensitive surface A is smaller than the area of ​​photosensitive surface B. Both photosensitive surface A and photosensitive surface B are square photosensitive surfaces.

[0035] First, it suppresses tremors caused by pulse beats. Photosensitive surfaces A and B are each installed at the same location near the blood vessels within the measurement area. Assuming other conditions are equal, the measurement results obtained from photosensitive surfaces A and B are compared. Here, the measurement results are expressed as the relative change in the light intensity value of the emitted light received by the photosensitive surface within one pulse cycle, or as the standard deviation of the light intensity value. The method for calculating the relative change in light intensity value is as described above and will not be explained again here. It was found that the relative change in the light intensity value of the emitted light received by photosensitive surface B is smaller than the relative change in the light intensity value of the emitted light received by photosensitive surface A, and the standard deviation of the light intensity value of the emitted light received by photosensitive surface B is smaller than the standard deviation of the light intensity value of the emitted light received by photosensitive surface A. From this, whether the measurement result is expressed as the relative change in the light intensity value of the emitted light received by the photosensitive surface or as the standard deviation of the light intensity value of the emitted light received by the photosensitive surface, it can be obtained that the measurement result obtained with photosensitive surface B is superior to the measurement result obtained with photosensitive surface A.

[0036] Since the measurement results obtained with photosensitive surface B are superior to those obtained with photosensitive surface A, and at the same time the area of ​​photosensitive surface B is larger than the area of ​​photosensitive surface A, it can be reflected that the larger the area of ​​the photosensitive surface, the better the effect of suppressing tremors caused by pulse beats.

[0037] Second, it is possible to suppress flickering caused by changes in the intensity distribution of light spots irradiated by incident light onto the measurement area. When other conditions remain unchanged, only the intensity distribution of the light spots irradiated by incident light onto the measurement area is altered. The measurement results obtained from photosensitive surface A and photosensitive surface B are compared, wherein the measurement results are expressed as the relative change in the light intensity value of the outgoing light received by the photosensitive surface within a preset time period, or as the standard deviation of the light intensity value. The method for calculating the relative change in light intensity value is as described above and will not be explained again here. It was found that the change in the light intensity value of the outgoing light received by photosensitive surface B is smaller than the change in the light intensity value of the outgoing light received by photosensitive surface A, and the standard deviation of the light intensity value of the outgoing light received by photosensitive surface B is smaller than the standard deviation of the light intensity value of the outgoing light received by photosensitive surface A. From this, whether the measurement result is expressed as the relative change in the light intensity value of the emitted light received by the photosensitive surface or as the standard deviation of the light intensity value of the emitted light received by the photosensitive surface, it can be obtained that the measurement result obtained with photosensitive surface B is superior to the measurement result obtained with photosensitive surface A.

[0038] Since the measurement results obtained with photosensitive surface B are superior to the measurement results obtained with photosensitive surface A, and at the same time the area of ​​photosensitive surface B is larger than the area of ​​photosensitive surface A, it can be reflected that the larger the area of ​​the photosensitive surface, the better the effect of suppressing shaking caused by changes in the intensity distribution of light spots irradiated by incident light onto the measurement area.

[0039] Third, it suppresses flickering caused by the uncertainty of incident light self-transmission. The Monte Carlo simulation method is applied. The number of photons is 10 15Central incidence is applied with incident light, photosensitive surface A and photosensitive surface B are each installed at a distance of 2.4 mm from the center of the incident light, and the number of simulations is 22. The measurement results obtained from photosensitive surface A and photosensitive surface B are compared, wherein the measurement results are expressed as the standard deviation of the number of emitted photons per unit area, reflecting that the smaller the standard deviation of the number of emitted photons per unit area, the better the suppression effect. Figure 4 schematically illustrates a schematic diagram of the measurement results obtained based on the Monte Carlo simulation method according to an embodiment of the present disclosure. It was found that the standard deviation of the number of emitted photons per unit area corresponding to photosensitive surface B is smaller than the standard deviation of the number of emitted photons per unit area corresponding to photosensitive surface A. That is, the measurement results obtained with photosensitive surface B are superior to the measurement results obtained with photosensitive surface A.

[0040] Since the measurement results obtained with photosensitive surface B are superior to those obtained with photosensitive surface A, and at the same time the area of ​​photosensitive surface B is larger than the area of ​​photosensitive surface A, it can be reflected that the larger the area of ​​the applied photosensitive surface, the better the effect of suppressing shaking caused by the uncertainty of the transmission of incident light itself.

[0041] Through the examples of the three aspects above, it can be reflected that the larger the area of ​​the photosensitive surface, the better the effect of suppressing the adverse influence of vibration on the measurement results.

[0042] According to an embodiment of the present disclosure, each photosensitive surface may be installed as an annular photosensitive surface or a non-annular photosensitive surface, wherein the non-annular photosensitive surface may include a fan-shaped ring photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface. The polygonal photosensitive surface may include a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

[0043] According to an embodiment of the present disclosure, each of the M photosensitive surfaces may be used alone, partially combined, or fully combined, and combined use reflects the output of a single output light intensity. In an embodiment of the present disclosure, a photosensitive surface for outputting a single output light intensity is referred to as a homogeneous photosensitive surface, and a homogeneous photosensitive surface may include one or a plurality of photosensitive surfaces. Here, the condition for combining different photosensitive surfaces may be that the average optical path length of the emitted light received by each photosensitive surface is within an average optical path length range. The average optical path length range may be a range configured to be greater than or equal to a first average optical path length limit and less than or equal to a second average optical path length limit. The first average optical path length limit and the second average optical path length limit may be determined based on the average optical path length and the range of variation in optical path length. The average optical path length is an average value calculated based on the average optical path length of the emitted light received by each photosensitive position of the homogeneous photosensitive surface. For example, if the average optical path length is a and the variation range of the optical path length is ±30%, the first average optical path length limit may be 0.7a and the second average optical path length limit may be 1.3a.

[0044] The average optical path length is described as follows. The transmission path of light in a tissue can be represented by the optical path length and the penetration depth, where the optical path length represents the total distance over which light is transmitted in the tissue, and the penetration depth represents the maximum longitudinal distance that light can reach in the tissue. The average optical path length represents the average value of the optical path lengths of light in the tissue for a determined source detection distance. The probability distribution function of the optical path length can be understood as a function of the source detection distance and the tissue optical parameters, where the source detection distance represents the radial distance between the center of the incident light and the center of the photosensitive plane. Correspondingly, in mathematical expression, the average optical path length can be understood as a function of the source detection distance and the tissue optical parameters, where the tissue optical parameters may include the absorption coefficient, the scattering coefficient, and the anisotropy factor. Factors influencing the average optical path length may include the absorption coefficient, the scattering coefficient, the anisotropy factor, and the source detection distance.

[0045] According to an embodiment of the present disclosure, a homogeneous photosensitive surface may be an annular photosensitive surface or a non-annular photosensitive surface. A homogeneous photosensitive surface is defined as an annular photosensitive surface, wherein when the homogeneous photosensitive surface comprises a single photosensitive surface, the homogeneous photosensitive surface may be an independent annular photosensitive surface. Where the homogeneous photosensitive surface comprises a plurality of photosensitive surfaces, the homogeneous photosensitive surface is an annular photosensitive surface formed by a combination of the plurality of photosensitive surfaces. A homogeneous photosensitive surface is defined as a non-annular photosensitive surface, wherein when the homogeneous photosensitive surface comprises a single photosensitive surface, the homogeneous photosensitive surface may be an independent non-annular photosensitive surface. Where the homogeneous photosensitive surface comprises a plurality of photosensitive surfaces, the homogeneous photosensitive surface is a non-annular photosensitive surface formed by a combination of the plurality of photosensitive surfaces.

[0046] In operation S330, the concentration of the tissue component to be measured is determined according to at least one output light intensity corresponding to a plurality of preset wavelengths.

[0047] According to an embodiment of the present disclosure, after obtaining at least one output light intensity corresponding to at least one preset wavelength, the concentration of a tissue component to be measured can be determined by applying an external disturbance suppression method to process the at least one output light intensity corresponding to at least one preset wavelength. Here, the external disturbance suppression method may include a differential measurement method. The differential measurement method may include a time differential measurement method, a position differential measurement method, or a wavelength differential measurement method. Alternatively, the concentration of a tissue component to be measured may be determined by applying a non-differential measurement method to process at least one output light intensity. Each output light intensity may include diffuse scattering light intensity or diffuse transmission light intensity.

[0048] According to the technical method of the embodiment of the present disclosure, the photosensitive surface can collect light intensity values ​​of the emitted light emitted from an emission position within a corresponding preset anti-vibration range. Since the photosensitive surface having the above-described characteristics has improved the ratio of the area capable of stably receiving the emitted light to the area of ​​the photosensitive surface, the stability of receiving the emitted light has been improved, and furthermore, the adverse effect of changes in the intensity distribution of the emitted light caused by vibration can be reduced, thereby improving measurement precision.

[0049] According to an embodiment of the present disclosure, the ratio of the average optical path length of the emitted light received by each photosensitive surface in the target tissue layer to the total optical path length is greater than or equal to a ratio limit, wherein the total optical path length is the total distance the emitted light is transmitted within the measurement area.

[0050] According to an embodiment of the present disclosure, the tissue model of the subject to measurement generally has a layered structure, that is, it can be divided into one layer or multiple layers. Meanwhile, the information regarding the tissue component to be measured possessed by different tissue layers is different. To improve measurement precision, the transmission path of the emitted light should preferably pass mainly through a tissue layer that is relatively rich in information regarding the tissue component to be measured. The target tissue layer can be understood as a tissue layer that is relatively rich in information regarding the tissue component to be measured or a tissue layer that is the main source of the tissue component to be measured. The following is an explanation using an example where the subject to be measured is the human body and the tissue component to be measured is blood glucose.

[0051] The human skin tissue model can be understood as a three-layer model from the outside in, consisting of the epidermis, dermis, and subcutaneous fat layer. Here, the epidermis contains a small amount of tissue fluid and does not contain plasma or lymph. The dermis contains a large amount of tissue fluid and, due to the presence of abundant capillaries, also contains a relatively large amount of plasma and a small amount of lymph. The subcutaneous fat layer contains a small amount of cellular fluid and, due to the presence of blood vessels such as veins and arteries, contains a large amount of plasma and a small amount of lymph. From this, it can be seen that the information regarding the tissue components to be measured differs between the different tissue layers.

[0052] The epidermal layer is not a suitable source of blood glucose information because it contains a small amount of tissue fluid. The subcutaneous fat layer contains a large amount of plasma and a relatively small amount of tissue fluid, but it is also not a suitable source of blood glucose information because it is subject to limitations in the penetration depth of incident light. The dermal layer can be used as a primary source of blood glucose information because it contains abundant capillaries and a large amount of tissue fluid, and incident light can reach the dermal layer relatively easily. Accordingly, the target tissue layer may be the dermal layer.

[0053] According to an embodiment of the present disclosure, the average optical path length of the emitted light in each tissue layer can be determined according to the optical path length and the penetration depth.

[0054] In order to ensure that the transmission path of the emitted light is preferably one that passes mainly through the target tissue layer, the ratio of the average optical path length in the target tissue layer for the emitted light received by each photosensitive surface to the total optical path length must be greater than or equal to a ratio limit, where the total optical path length is the total distance the emitted light is transmitted within the measurement area, that is, the total distance of the path traversed by the incident light from entering the measurement area, being transmitted within the measurement area, to reaching the emission position. Here, the ratio limit is related to the source detection distance between the center of the photosensitive surface and the center of the incident light and the tissue optical parameters.

[0055] Since the embodiment of the present disclosure limits the ratio of the average optical path length in the target tissue layer to the total optical path length for the emitted light received by the photosensitive surface, it should be noted that the area of ​​the photosensitive surface of the embodiment of the present disclosure should not be too large, and the area of ​​the photosensitive surface is a large area within the area range.

[0056] According to an embodiment of the present disclosure, the method may further include the following operations.

[0057] Depending on the tissue structure characteristics within the measurement area, one or more photosensitive surfaces are included, and the total area of ​​the same photosensitive surfaces is determined to output a single output light intensity.

[0058] According to an embodiment of the present disclosure, the total area of ​​the same photosensitive surface can be determined according to the tissue composition characteristics within the measurement area. Here, the tissue structure characteristics can be understood as structural characteristics possessed by the measurement area.

[0059] For example, if the measurement area is an area where three blood vessels intersect, and a co-flow photosensitive surface is installed in the area where three blood vessels intersect, the total area of ​​the co-flow photosensitive surface is limited by the area of ​​the area where three blood vessels intersect. In other words, the total area of ​​the co-flow photosensitive surface must be determined according to the area of ​​the area where three blood vessels intersect.

[0060] For example, if the measurement area is the area where the finger is located and a homogeneous photosensitive surface is installed in that area, the total area of ​​the homogeneous photosensitive surface is limited by the area where the finger is located. In other words, the total area of ​​the homogeneous photosensitive surface must be determined based on the area where the finger is located.

[0061] In the embodiments of the present disclosure, the area of ​​the photosensitive surface may be determined according to the tissue composition characteristics; however, since the area determined according to the tissue composition characteristics should generally not be too large, it should be noted that the area of ​​the photosensitive surface in the embodiments of the present disclosure should not be too large and that the area of ​​the photosensitive surface is a large area within the area range.

[0062] According to an embodiment of the present disclosure, the ratio of the area of ​​each photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to a ratio limit.

[0063] According to an embodiment of the present disclosure, in order to reduce the influence of uncertainty in incident light transmission, randomness of the light source, physiological background fluctuations, and vibrations caused by pulses on the distribution of incident light in the measurement area, the ratio of the area of ​​the photosensitive surface to the perimeter of the photosensitive surface can be made as large as possible. That is, the reasons why the ratio is greater than or equal to the ratio limit are as follows.

[0064] For the sake of convenience, the photosensitive surface is divided into two parts below: the edge portion and the non-edge portion (or inner portion). Generally, vibration primarily affects the emitted light collected at the edge portion, whereas the impact on the non-edge portion is relatively small. In other words, the non-edge portion can collect emitted light relatively stably. To understand this from another perspective, when vibration is present, minute changes occur in the intensity distribution of the emitted light within the measurement area; consequently, the light intensity value of the emitted light received by the edge portion undergoes relatively large variations depending on the intensity distribution. However, since the emitted light located at the non-edge portion can mostly be collected by the photosensitive surface relatively stably, the light intensity value of the emitted light received by the non-edge portion remains relatively stable. Therefore, to effectively suppress the adverse effects of vibration on the measurement results, the ratio of the area corresponding to the non-edge portion to the area of ​​the photosensitive surface can be made as large as possible; the larger the ratio, the better the effect of weakening the adverse effects. Here, the edge portion can be represented as the perimeter of the photosensitive surface, and the non-edge portion as the area of ​​the photosensitive surface. Therefore, the ratio of the area of ​​the photosensitive surface to the perimeter of the photosensitive surface can be made as large as possible.

[0065] For example, when photosensitive surface 1 is a circular photosensitive surface and photosensitive surface 2 is a square photosensitive surface and the perimeters are the same, since the area of ​​photosensitive surface 1 is larger than the area of ​​photosensitive surface 2, the ratio of the area to the perimeter of photosensitive surface 1 is greater than the ratio of the area to the perimeter of photosensitive surface 2, and therefore the effect of photosensitive surface 1 in weakening adverse effects is better than the effect of photosensitive surface 2 in weakening adverse effects.

[0066] It should be noted that the ratio of the photosensitive surface area to its perimeter being greater than or equal to the ratio limit explains that the condition of the photosensitive surface area being greater than or equal to the area limit is satisfied. For most photosensitive surface shapes, if the ratio of the photosensitive surface area to its perimeter is generally greater than or equal to the ratio limit, the actual size of the photosensitive surface area is also limited. This is because, generally for most shapes, the ratio of the shape's area to its perimeter has a positive correlation with the size of the area. In other words, the larger the ratio of the shape's area to its perimeter, the larger the shape's area.

[0067] For example, in the case of a circle, the area of ​​the circle is πR 2 And, the ratio of the area to the perimeter of a circle is R / 2, where R represents the radius. Since the size of the ratio of the area to the perimeter of a circle is related only to the radius, and the size of the area of ​​a circle is related only to the radius, the ratio of the area to the perimeter of a circle has a positive correlation with the size of the area, and limiting the ratio of the area to the perimeter of a circle limits the size of the area of ​​the circle as well. Also, in the case of a square, the area of ​​the square is a 2 And, the ratio of the area to the perimeter of the square is a / 4, where a represents the length of the side. Since the size of the ratio of the area to the perimeter of the square is related only to the length of the side, and the size of the area of ​​the square is related only to the length of the side, the area of ​​the square has a positive correlation with the ratio of the perimeter and the size of the area, and if the ratio of the area to the perimeter of the square is limited, the size of the area of ​​the square is also limited.

[0068] According to an embodiment of the present disclosure, the ratio limit is greater than or equal to 0.04 mm.

[0069] 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 within the area range. The following describes the situation.

[0070] First, the area of ​​the photosensitive surface must not be too small. Since the large-area photosensitive surface of the embodiment of the present disclosure refers to a photosensitive surface whose area enables the photosensitive surface to collect the light intensity of the light emitted from an emission position within a preset anti-shake range, the large area among the large-area photosensitive surfaces of the embodiment of the present disclosure is a large area for implementing anti-shake. At the same time, the ratio of the area of ​​the photosensitive surface to the perimeter of the photosensitive surface indicates that the area of ​​the photosensitive surface enables the photosensitive surface to collect the light intensity value of the light emitted from an emission position within a preset anti-shake range. Meanwhile, in general, since the ratio of the area of ​​the photosensitive surface to the perimeter has a positive correlation with the area of ​​the photosensitive surface, 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 limit, the size of the area of ​​the photosensitive surface is also actually limited. In other words, the ratio of the photosensitive surface area to the perimeter can be set so that the photosensitive surface area must not be too small, by ensuring that the ratio is greater than or equal to the ratio limit.

[0071] Second, the area of ​​the photosensitive surface must not be too large. Embodiments of the present disclosure require that the ratio of the average optical path length in the target tissue layer to the total optical path length of the emitted light received by the photosensitive surface is greater than or equal to a ratio limit, and / or that the area of ​​the photosensitive surface be determined according to the tissue composition characteristics, and as described above, the area of ​​the photosensitive surface must not be too large.

[0072] From this, it can be explained that the area of ​​the photosensitive surface of the embodiment of the present disclosure is a relative large area, that is, a large area within the area range.

[0073] Furthermore, there may be cases where the ratio of the photosensitive surface area to the perimeter is not large because the photosensitive surface area is relatively large but the perimeter is also relatively large. In other words, since the ratio of the photosensitive surface area to the perimeter is smaller than the ratio threshold, it may be difficult to satisfy the anti-shake requirements even for an absolutely large photosensitive surface. Additionally, there may be cases where the photosensitive surface area is too small and the perimeter is relatively large, causing the ratio to be smaller than the ratio threshold; therefore, it is also difficult to satisfy the anti-shake requirements when the photosensitive surface area is too small.

[0074] According to an embodiment of the present disclosure, the photosensitive surface is in contact with or not in contact with the surface of the measurement area.

[0075] According to an embodiment of the present disclosure, the form of tissue component measurement may include contact measurement and non-contact measurement. Here, contact measurement can avoid external warm light being received by the photosensitive surface and further improve measurement precision. Non-contact measurement can avoid the influence of external warming factors, such as temperature and pressure, on the measurement result and further improve measurement precision.

[0076] If the photosensitive surface is installed to be in contact with the surface of the measurement area, the form of tissue component measurement can be considered a contact measurement. If the photosensitive surface is installed to be non-contact with the surface of the measurement area, the form of tissue component measurement can be considered a non-contact measurement.

[0077] According to an embodiment of the present disclosure, the distance between the photosensitive surface and the surface of the measurement area is less than or equal to a first distance limit, and the efficiency of the photosensitive surface receiving the emitted light is greater than or equal to an efficiency limit.

[0078] According to an embodiment of the present disclosure, since the photosensitive surface is made of a photosensitive material and the area of ​​the photosensitive surface is continuous, it is possible to achieve reception of a wide range of light intensity values ​​and improve the efficiency of receiving emitted light. Based on this, it is possible to achieve an efficiency of receiving emitted light that is greater than or equal to an efficiency limit even when the photosensitive surface is close to the surface of the measurement area, that is, when the distance from the surface of the measurement area is less than or equal to a first distance limit.

[0079] According to an embodiment of the present disclosure, determining the concentration of a tissue component to be measured according to at least one output light intensity corresponding to a plurality of preset wavelengths may include the following operations.

[0080] For each preset wavelength among a plurality of preset wavelengths, a first output light intensity and a second output light intensity are determined from at least two output light intensities corresponding to the preset wavelength, and the concentration of the tissue component to be measured is determined according to the first output light intensity and the second output light intensity corresponding to each preset wavelength.

[0081] According to an embodiment of the present disclosure, the average optical path length of the emitted light corresponding to the first output light intensity and the average optical path length of the emitted light corresponding to the second output light intensity are different. For each tissue component to be measured, the concentration of the tissue component to be measured can be determined according to the first output light intensity and the second output light intensity corresponding to each preset wavelength.

[0082] According to an embodiment of the present disclosure, determining the concentration of a tissue component to be measured according to a first output light intensity and a second output light intensity corresponding to each preset wavelength may include the following operations.

[0083] A difference signal is obtained by performing a difference process on the first output light intensity and the second output light intensity corresponding to a preset wavelength, and the concentration of the tissue component to be measured is determined according to the difference signal corresponding to each preset wavelength.

[0084] According to an embodiment of the present disclosure, since uncontrollable fluctuations in measurement conditions are difficult to predict and possess uncontrollable characteristics, it is difficult to reduce the impact of such fluctuations on measurement results by applying an effective control method to achieve reproducibility. To improve measurement precision, the inventors have discovered that by applying a reasonable mathematical algorithm, the impact of uncontrollable fluctuations on measurement results can be reduced to a negligible level. In other words, the impact of uncontrollable fluctuations on measurement results is made to correspond to the level of impact of random noise on measurement results.

[0085] To reduce the impact of uncontrollable variations in measurement conditions on the measurement results, an external disturbance suppression method including a differential measurement method can be applied. The differential measurement method may include a time differential measurement method and a position differential measurement method. The reason the differential measurement method can reduce the impact of uncontrollable variations in measurement conditions on the measurement results is that if the external disturbance information possessed by the output light intensity at different average optical path lengths is fundamentally the same—that is, if the influence of external disturbance received by the output light intensity at different average optical path lengths is fundamentally consistent—then the effective information possessed by the output light intensity at different average optical path lengths is different. Consequently, the output light intensities at two average optical path lengths (i.e., the first output light intensity and the second output light intensity) can be differentially processed to obtain a differential signal, and the concentration of the tissue component under measurement can be determined based on the differential signal. Here, the external disturbance information can be understood as the output light intensity's response to external disturbance. The effective information can be understood as the output light intensity's response to the tissue component under measurement.

[0086] According to an embodiment of the present disclosure, the difference processing among the difference processing of a first output light intensity and a second output light intensity corresponding to a preset wavelength may include a hardware-side processing method and a software-side processing method. Here, the hardware-side processing method may include processing that applies a difference circuit. Here, the software-side processing method may include a difference operation that applies a difference algorithm. The difference algorithm may include a direct difference operation and a logarithmic difference operation. Here, a direct difference operation refers to directly differentiating two parameters. A logarithmic difference operation refers to first performing a logarithmic operation on two parameters to obtain parameters after logarithm calculation, and then differentiating the two parameters after logarithm calculation.

[0087] According to an embodiment of the present disclosure, the difference measurement method effectively attenuates common-mode external information and further improves measurement precision.

[0088] According to an embodiment of the present disclosure, obtaining a difference signal by differential processing a first output light intensity and a second output light intensity corresponding to a preset wavelength may include the following operations.

[0089] A difference circuit is applied to process the first output light intensity and the second output light intensity corresponding to a preset wavelength to obtain a difference signal.

[0090] According to an embodiment of the present disclosure, a difference signal can be directly obtained by applying a difference circuit to implement difference processing for a first output light intensity and a second output light intensity.

[0091] According to an embodiment of the present disclosure, obtaining a difference signal by differential processing a first output light intensity and a second output light intensity corresponding to a preset wavelength may include the following operations.

[0092] A difference signal is obtained by applying a difference algorithm to process the first output light intensity and the second output light intensity corresponding to a preset wavelength.

[0093] According to an embodiment of the present disclosure, obtaining a difference signal by applying a difference algorithm to process a first output light intensity and a second output light intensity corresponding to a preset wavelength may include the following operations.

[0094] A difference signal is obtained by directly performing a difference operation on the first output light intensity and the second output light intensity corresponding to a preset wavelength.

[0095] According to an embodiment of the present disclosure, obtaining a difference signal by applying a difference algorithm to process a first output light intensity and a second output light intensity corresponding to a preset wavelength may include the following operations.

[0096] A first output light intensity and a second output light intensity corresponding to a preset wavelength are processed by logarithm calculation to obtain a first logarithmic light intensity and a second logarithmic light intensity, and a difference signal is obtained by directly performing a difference operation on the first logarithmic light intensity and the second logarithmic light intensity corresponding to the preset wavelength.

[0097] According to an embodiment of the present disclosure, the first log light intensity represents the log of the first output light intensity, and the second log light intensity represents the log of the second output light intensity.

[0098] The difference signal can be determined through the following equation (1).

[0099] (1)

[0100] Here, represents the difference signal, represents the first output light intensity, represents the second output light intensity. represents the average optical path length corresponding to the first output light intensity, and represents the average optical path length corresponding to the second output light.

[0101] According to an embodiment of the present disclosure, a first output light intensity and a second output light intensity are obtained by collecting at different times by identical or different cognate photosensitive surfaces. The first output light intensity is the light intensity of the systole, and the second output light intensity is the light intensity of the expansion phase. A cognate photosensitive surface comprises one or a plurality of photosensitive surfaces, and the cognate photosensitive surface is intended to output a single output light intensity.

[0102] According to an embodiment of the present disclosure, when a first output light intensity and a second output light intensity are identical or obtained by being collected at different times by different photosensitive surfaces, a time difference measurement method based on pulse waves can be applied to perform tissue component measurement.

[0103] A pulse is an arterial beat in which periodic contraction and expansion occur in accordance with the heartbeat; pressure within the major artery causes pulsatile changes in the diameter of the blood vessel, and consequently, the blood flow volume within the vessel also undergoes regular and periodic changes. Each pulse waveform includes one rising branch and one falling branch; here, the rising branch represents the expansion of the artery during ventricular systole, and the falling branch represents the contraction of the artery during ventricular diastole. One expansion and one contraction of the ventricle represent one pulse cycle.

[0104] According to an embodiment of the present disclosure, since pulse information must be utilized when applying a time difference measurement method based on pulse waves, a photosensitive surface can be installed as close as possible to a target area (e.g., a target blood vessel) to improve measurement precision. That is, a photosensitive surface of the same type for outputting a first output light intensity and a second output light intensity can be installed at a location where the distance from the target area is less than or equal to a fourth distance limit. Here, the fourth distance limit may be 0. That is, the photosensitive surface of the same type can be installed at the target area. Installing a photosensitive surface of the same type for outputting a first output light intensity and a second output light intensity at a location where the distance from the target area is less than or equal to a fourth distance limit means that the distance from the target area of ​​each photosensitive surface among the photosensitive surfaces for outputting a first output light intensity and a second output light intensity is less than or equal to a fourth distance limit. The distance between each photosensitive surface among the like photosensitive surfaces and the target area is less than or equal to the fourth distance limit. This may be because the distance between the edge of the photosensitive surface furthest from the target area and the target blood vessel is less than or equal to the fourth distance limit.

[0105] The requirement to utilize pulse information as much as possible when applying a time-difference measurement method based on pulse waves does not contradict the aforementioned application of a large-area photosensitive surface to reduce the adverse effects of pulse beats on the measurement. The former aims to utilize useful information resulting from pulse beats as much as possible, while the latter aims to reduce the adverse effects caused by pulse beats as much as possible. Additionally, the first output light intensity may be the diastolic light intensity, and the second output light intensity may be the systolic light intensity. The first and second output light intensities corresponding to a preset wavelength may be output light intensities within the same pulse period, or they may be output light intensities within different pulse periods.

[0106] According to an embodiment of the present disclosure, a first output light intensity corresponding to a preset wavelength is obtained by collecting a first photosensitive surface corresponding to the preset wavelength, and a second output light intensity corresponding to the preset wavelength is obtained by collecting a second photosensitive surface corresponding to the preset wavelength. The first photosensitive surface includes one or more photosensitive surfaces, and the second photosensitive surface includes one or more photosensitive surfaces.

[0107] According to an embodiment of the present disclosure, for a preset wavelength, there is a first photosensitive surface and a second photosensitive surface corresponding to the preset wavelength. Here, the first photosensitive surface is for outputting a first output light intensity corresponding to the preset wavelength, and the second photosensitive surface is for outputting a second output light intensity corresponding to the preset wavelength. Both the first photosensitive surface and the second photosensitive surface may include one or a plurality of photosensitive surfaces.

[0108] According to an embodiment of the present disclosure, the concentration of a tissue component to be measured can be determined by applying a position difference measurement method to process a first output light intensity and a second output light intensity.

[0109] According to an embodiment of the present disclosure, since the target area (e.g., target blood vessel) must be avoided as much as possible when applying the position difference measurement method, the photosensitive surface may be installed as far as possible from the target area to improve measurement precision. That is, a first photosensitive surface for outputting a first output light intensity may be installed at a location where the distance from the target area is greater than or equal to a fifth distance limit. In other words, the distance from the target area of ​​each photosensitive surface among the first photosensitive surfaces is greater than or equal to the fifth distance limit. The distance from the target area of ​​each photosensitive surface among the first photosensitive surfaces is greater than or equal to the fifth distance limit, which may be such that the distance from the target area of ​​the edge of the photosensitive surface closest to the target area among the first photosensitive surfaces is greater than or equal to the fifth distance limit. Furthermore, the first photosensitive surface and the target area do not come into contact, and the distance from the target area of ​​the center of the photosensitive surface closest to the target area among the first photosensitive surfaces is greater than or equal to the fifth distance limit. A photosensitive surface for outputting a second output light intensity is installed at a location where the distance from the target area is greater than or equal to the sixth distance limit. For an understanding of installing the second photosensitive surface for outputting the second output light intensity at a location where the distance from the target area is greater than or equal to the sixth distance limit, refer to the description of the first photosensitive surface of the same type for outputting the first output light intensity, which is not explained again here.

[0110] According to an embodiment of the present disclosure, the average optical path length of the emitted light received at different photosensitive positions of each photosensitive surface among the first similar photosensitive surfaces falls within a first average optical path length range determined according to the first average optical path length. The first average optical path length is an average value obtained by calculating the average optical path length of the emitted light received at each photosensitive position of the first similar photosensitive surfaces. The average optical path length of the emitted light received at different photosensitive positions of each photosensitive surface among the second similar photosensitive surfaces falls within a second average optical path length range determined according to the second average optical path length. The second average optical path length is an average value obtained by calculating the average optical path length of the emitted light received at each photosensitive position of the second similar photosensitive surfaces.

[0111] According to an embodiment of the present disclosure, in order to improve the measurement precision of tissue component measurement based on a position difference measurement method, it is necessary to ensure that the emitted light received by the first photosensitive surface has the characteristics of a near-path length and that the emitted light intensity received by the second photosensitive surface has the characteristics of a near-path length. A near-path length can be understood as the average path length of the emitted light being within the average path length range.

[0112] For a first similar photosensitive surface, the average optical path length of the emitted light received at different photosensitive positions of each photosensitive surface among the first similar photosensitive surfaces falls within a first average optical path length range. Here, the first average optical path length range can be determined by a method of determining the first average optical path length of the average optical path length of the emitted light received at each photosensitive position of the first similar photosensitive surface, determining the range of variation of the first optical path length, and determining the first average optical path length range according to the first average optical path length and the range of variation of the first optical path length. For example, if the first average optical path length is b and the first optical path length range of variation is ±40%, the first average optical path length range is greater than or equal to 0.6b and less than or equal to 1.4b.

[0113] For a second photosensitive surface of the same type, the average optical path length of the emitted light received at different photosensitive positions of each photosensitive surface among the second photosensitive surfaces falls within a second average optical path length range. Here, the second average optical path length range can be determined by a method of determining the average value of the second optical path length of the average optical path length of the emitted light received at each photosensitive position of the second photosensitive surface, determining the range of variation of the second optical path length, and determining the second average optical path length range according to the average value of the second optical path length and the range of variation of the second optical path length.

[0114] According to an embodiment of the present disclosure, the absolute value of the difference between the average value of the first optical path length and the average value of the second optical path length falls within the range of the difference between the first optical path lengths.

[0115] According to an embodiment of the present disclosure, in order to improve the measurement precision of tissue component measurement based on a differential measurement method, a first photosensitive surface and a second photosensitive surface must be installed within an appropriate positional range. The following is an explanation using the example where the tissue component to be measured is blood glucose. Regarding the case where the tissue component to be measured is blood glucose, the target tissue layer is the dermis, and the output light intensity is required to be an output light intensity that primarily contains information on the tissue component within the dermis.

[0116] First, if the distance between the position of the photosensitive surface and the center of the incident light is too small, the output light intensity of the emitted light mainly contains information on tissue components in the epidermal layer, that is, blood glucose information. If the distance between the position of the photosensitive surface and the center of the incident light is too large, the output light intensity of the emitted light mainly contains information on tissue components in the subcutaneous fat layer. The dermis is located between the epidermal layer and the subcutaneous fat layer. From this, it can be seen that the setting positions of the first photosensitive surface and the second photosensitive surface must be selected within a single appropriate position range, and the distance between the first photosensitive surface and the second photosensitive surface must not be too large.

[0117] Second, while the difference measurement method can effectively attenuate common mode disturbances, it may also lose some valid information, namely blood glucose information, while attenuating common mode disturbances. If the two locations are very close, all valid information may be lost. From this, it can be seen that the setting locations of the first co-photosensitive surface and the second co-photosensitive surface must be selected within a single appropriate location range, and the distance between the first co-photosensitive surface and the second co-photosensitive surface must not be too small.

[0118] To implement the installation of the first and second co-photosensitive surfaces within a reasonable positional range, this can be determined based on the principles of valid information measurement, differential measurement precision optimization, and effective removal of external disturbances. Here, the valid information measurement principle implies that the emitted light from the two locations should contain as much information as possible regarding tissue components within the target tissue layer. Therefore, the two locations must be within a reasonable positional range. The differential measurement precision optimization principle implies ensuring that as much valid information as possible is retained even after differential measurement. To achieve this, a certain distance must be maintained between the two locations. The principle of effective removal of external disturbances implies enhancing the effect of removing common mode disturbances in the differential measurement method. To achieve this, the distance between the two locations should be as small as possible.

[0119] Installing the first and second like photosensitive surfaces within a reasonable positional range is reflected in the optical path length; that is, the absolute value of the difference between the average value of the first optical path length corresponding to the first like photosensitive surface and the average value of the second optical path length corresponding to the second like photosensitive surface falls within the first optical path length difference range. Here, the first optical path length difference range is determined according to the optimal difference optical path length. The optimal difference optical path length may be determined according to at least one of the three principles described above.

[0120] Likewise, regarding the positional installation requirements for the first and second photosensitive surfaces, it is required that the area of ​​the photosensitive surfaces not be too large; otherwise, it can be understood that this affects the difference effect and, furthermore, affects the measurement precision.

[0121] According to an embodiment of the present disclosure, the first average optical path length range is smaller than or equal to the first optical path length difference range, and the second average optical path length range is smaller than or equal to the first optical path length difference range.

[0122] According to an embodiment of the present disclosure, in order to implement the installation of a first photosensitive surface and a second photosensitive surface within a reasonable positional range, when reflected in the optical path length, it must be ensured that the first average optical path length range is less than or equal to the first optical path length difference range, and the second average optical path length range is less than or equal to the first optical path length difference range. From this, it is possible to obtain that the absolute value of the difference between the first optical path length average value corresponding to the first photosensitive surface and the second optical path length average value corresponding to the second photosensitive surface falls within the first optical path length difference range, the first average optical path length range is less than or equal to the first optical path length difference range, and the second average optical path length range is less than or equal to the first optical path length difference range.

[0123] According to an embodiment of the present disclosure, the first optical path length difference range is determined according to the optimal difference optical path length corresponding to a preset wavelength.

[0124] According to an embodiment of the present disclosure, when the measurement area of ​​a subject to be measured is determined, there exists an optimal difference sensitivity corresponding to the preset wavelength. The optimal difference sensitivity may represent the sensitivity corresponding to the maximum change in the difference signal caused by a change in the concentration of a unit tissue component to be measured. The optimal difference optical path length can be determined according to the optimal difference sensitivity. That is, the optimal difference optical path length can be determined according to the principle of optimizing difference measurement precision, and thus the optical path length corresponding to the optimal difference sensitivity can be called the optimal difference optical path length.

[0125] According to an embodiment of the present disclosure, after determining an optimal difference optical path length corresponding to a preset wavelength, an upper and lower adjustment range can be set, and a first optical path length difference range corresponding to a preset wavelength can be determined according to the optimal difference optical path length corresponding to the preset wavelength and the upper and lower adjustment range.

[0126] According to an embodiment of the present disclosure, the source detection distance of each photosensitive surface among the first photosensitive surfaces corresponding to a preset wavelength, which is located away from the center of the incident light, is within the source detection distance range corresponding to the preset wavelength. Here, the source detection distance range is determined according to the source detection distance of the flow reference position corresponding to the preset wavelength, which is located away from the center of the incident light.

[0127] According to an embodiment of the present disclosure, the position of the photosensitive surface can be set based on a flow reference method to further improve measurement precision. Here, the flow reference method is described as follows.

[0128] Regarding the subject being measured, absorption and scattering effects may occur after incident light enters the tissue. Absorption can directly cause the attenuation of light energy, while scattering changes the direction of photon transmission, affecting the distribution of the emitted light; the distribution of the emitted light is the result of the combined action of both. Based on the flow reference method, regarding the tissue component being measured, there exists a specific location located away from the center of the incident light. At this location, the degree of influence that absorption and scattering have on the output light intensity of the emitted light is the same, but the directions are opposite; consequently, the emitted light becomes insensitive to changes in the concentration of the tissue component being measured. A location possessing the aforementioned characteristics can be referred to as a reference location (or reference position). The output light intensity of the emitted light at the reference location reflects the response to external disturbances other than the tissue component being measured during the measurement process. Simultaneously, regarding the tissue component being measured, there exists a specific location located away from the center of the incident light, and the sensitivity of the output light intensity of the emitted light at that location to changes in the concentration of the tissue component being measured is greater than or equal to the sensitivity limit. A location possessing the aforementioned characteristics can be referred to as the measurement location. The output light intensity of the emitted light at the measurement location reflects the response of the tissue components under measurement and the response to external disturbances other than the tissue components under measurement during the measurement process. Furthermore, the reference location and the measurement location differ depending on the wavelength, the object under measurement, and the measurement area. Therefore, the reference location can be referred to as a variable reference location.

[0129] According to an embodiment of the present disclosure, since the output light intensity of the emitted light from the flow reference position primarily has a response to external disturbances other than the tissue components being measured during the measurement process, the output light intensity of the emitted light from the flow reference position can be introduced into the differential measurement to attenuate common mode external disturbances as much as possible and to minimize the loss of effective information. Based on the above description, when the measurement area of ​​the object to be measured is determined, for each preset wavelength, at least one of the M photosensitive surfaces has a source detection distance from the center of the incident light that exists within a preset source detection distance range corresponding to the preset wavelength, and the preset source detection distance range is determined according to the source detection distance from the center of the incident light of the flow reference position corresponding to the preset wavelength. According to an embodiment of the present disclosure, the source detection distance from the center of the incident light of each photosensitive surface among the first similar photosensitive surfaces can be made to be within a source detection distance range corresponding to the preset wavelength.

[0130] For example, for measurement area B of object A to be measured, if the distance from the center of the incident light to the flow reference position corresponding to the preset wavelength λ1 is 1.7 mm, the preset source distance range corresponding to the preset wavelength λ1 may be 1.5 mm to 1.9 mm.

[0131] Based on the above description, a photosensitive surface corresponding to a reference position and a photosensitive surface corresponding to a measurement position are determined, and the output light intensity collected by the photosensitive surface corresponding to the reference position may be called the first output light intensity, and the output light intensity collected by the photosensitive surface corresponding to the measurement area may be called the second output light intensity. Alternatively, the output light intensity collected by the photosensitive surface corresponding to the measurement area may be called the first output light intensity, and the output light intensity collected by the photosensitive surface corresponding to the reference area may be called the second output light intensity.

[0132] According to an embodiment of the present disclosure, determining the concentration of a tissue component to be measured according to at least one output light intensity corresponding to a plurality of preset wavelengths may include the following operations.

[0133] For each preset wavelength among a plurality of preset wavelengths, a third output light intensity is determined from at least one output light intensity corresponding to the preset wavelength, and at least one difference signal is obtained by differential processing the third output light intensities corresponding to different preset wavelengths, and the concentration of the tissue component to be measured is determined according to the at least one difference signal.

[0134] According to an embodiment of the present disclosure, the concentration of a tissue component to be measured can be determined by processing a third output light intensity by applying a wavelength difference measurement method. If the following conditions are satisfied, the tissue component measurement is performed using the wavelength difference measurement method, thereby eliminating common mode disturbances while retaining a sufficient amount of valid information, and improving measurement precision.

[0135] First, for each tissue component under measurement, the law of the effect of the same external heat (e.g., temperature or pressure) on the output light intensity at two preset wavelengths is consistent or fundamentally consistent.

[0136] Second, there is a relatively large difference in sensitivity to changes in the concentration of the tissue component being measured between the output light intensity at two preset wavelengths.

[0137] When a preset wavelength is determined, a third output light intensity is determined at at least one output light intensity corresponding to the preset wavelength. In this way, the third output light intensity for each preset wavelength can be obtained. For two preset wavelengths, a difference signal can be obtained by performing a difference process on the two third output light intensities.

[0138] According to an embodiment of the present disclosure, differential processing of two third output light intensities may include processing the two third output light intensities by applying a differential circuit to obtain a differential signal, or applying a differential algorithm to perform a differential operation on the two third output light intensities to obtain a differential signal. Obtaining a differential signal by performing a differential operation on the two third output light intensities by applying a differential algorithm may include directly performing a differential operation on the two third output light intensities to obtain a differential signal, or processing the two third output light intensities to obtain two logarithmic light intensities, and directly performing a differential operation on the two logarithmic light intensities to obtain a differential signal.

[0139] According to an embodiment of the present disclosure, determining the concentration of a tissue component to be measured according to a difference signal corresponding to each preset wavelength may include the following operations.

[0140] At least one wavelength difference signal is obtained by directly performing a difference operation on difference signals corresponding to different preset wavelengths, and the concentration of the tissue component to be measured is determined according to at least one wavelength difference signal.

[0141] According to an embodiment of the present disclosure, the concentration of a tissue component to be measured can be determined by processing a difference signal using a wavelength difference measurement method. If the following conditions are satisfied, the tissue component measurement is performed using the wavelength difference measurement method, thereby eliminating common mode disturbances while retaining a sufficient amount of valid information, and improving measurement precision.

[0142] First, for each tissue component under measurement, the law of the effect of the same external disturbance (e.g., temperature or pressure) on the difference signal at two preset wavelengths is consistent or fundamentally consistent.

[0143] Second, there is a relatively large difference in sensitivity to changes in the concentration of tissue components measured between the two preset wavelengths.

[0144] For two preset wavelengths, a wavelength difference signal is obtained by directly performing a difference operation on the two difference signals, and the concentration of the tissue component to be measured can be determined based on at least one wavelength difference signal.

[0145] According to an embodiment of the present disclosure, determining the concentration of a tissue component to be measured according to at least one output light intensity corresponding to a plurality of preset wavelengths may include the following operations.

[0146] For each preset wavelength among a plurality of preset wavelengths, a fourth output light intensity is determined at at least one output light intensity corresponding to the preset wavelength, and the concentration of the tissue component to be measured is determined according to the fourth output light intensity corresponding to each preset wavelength.

[0147] According to an embodiment of the present disclosure, tissue component measurement can be performed by applying a method other than differential measurement. That is, the concentration of the tissue component to be measured is determined according to a fourth output light intensity corresponding to each preset wavelength.

[0148] According to an embodiment of the present disclosure, a fourth output light intensity corresponding to a preset wavelength is obtained by collecting from a photosensitive surface of the same type corresponding to the preset wavelength, and the difference between the average optical path length of the emitted light received at different photosensitive positions of each photosensitive surface among the same types of photosensitive surfaces and the optimal optical path length corresponding to the preset wavelength falls within a second optical path length difference range.

[0149] According to an embodiment of the present disclosure, when a measurement area of ​​a subject to be measured is determined to improve measurement precision, for each preset wavelength, the average optical path length of the emitted light received at different photosensitive positions on a photosensitive surface for collecting a third output light intensity can be made to approach the optimal optical path length corresponding to the preset wavelength. That is, the absolute value of the difference between the average optical path length of the emitted light received at different photosensitive positions on a photosensitive surface for collecting a third output light intensity and the optimal optical path length corresponding to the preset wavelength is made to be less than or equal to the second optical path length difference range. The optimal optical path length corresponding to the preset wavelength can be understood as the optical path length corresponding when the sensitivity of the tissue component to be measured is maximum at the preset wavelength.

[0150] According to an embodiment of the present disclosure, each photosensitive surface includes an annular photosensitive surface or a non-annular photosensitive surface, and the shapes of the different photosensitive surfaces are the same or different.

[0151] According to an embodiment of the present disclosure, each photosensitive surface may be manufactured from a photosensitive material. The ring-shaped photosensitive surface can avoid orientation positioning problems and can also enable the implementation of a design with a relatively large area within a relatively small source detection distance range. It should be noted that since the source detection distance is generally a relatively important physical quantity in biological tissue component measurements, implementing a design with a relatively large area within a relatively small source detection distance range is very rewarding.

[0152] According to an embodiment of the present disclosure, in some cases, the application of a non-circular photosensitive surface has the following beneficial effects.

[0153] First, since measurement results are influenced by the measurement area, installing the photosensitive surface in a measurement area favorable for measurement generally yields better results compared to installing it in a measurement area with external difficulties; therefore, the photosensitive surface can be installed in an appropriate location according to tissue composition characteristics. Since non-circular photosensitive surfaces can relatively easily avoid measurement areas with external difficulties, such as blood vessels or wound areas, applying non-circular photosensitive surfaces is relatively effective.

[0154] Second, due to tissue non-uniformity, the transmission path of the same incident light within the tissue may vary, and furthermore, the average optical path length corresponding to the emitted light from different emission locations may differ. Taking blood glucose as an example, since the dermis is generally the primary source of the blood glucose signal, the emitted light is required to be light obtained after being transmitted primarily from the dermis; accordingly, there is a certain requirement regarding the average optical path length corresponding to the emitted light.

[0155] Assuming that a ring-shaped photosensitive surface of a corresponding size is designed according to the requirements for average light intensity, the average optical path lengths corresponding to the emitted light received at different photosensitive locations on the ring-shaped photosensitive surface are fundamentally similar and consist mainly of emitted light passing through the dermis, and the average optical path lengths can be considered to be within the average light intensity range C. In this case, if the skin tissue is uniform, the above conclusion corresponds to actual situations. However, since skin tissue is generally not uniform, the difference in average optical path lengths corresponding to the emitted light received at different photosensitive locations on the same ring-shaped photosensitive surface becomes relatively large. For example, while the average optical path lengths corresponding to the emitted light received at some photosensitive locations on the ring-shaped photosensitive surface are fundamentally similar and all fall within the average optical path length range C, the average optical path lengths corresponding to the emitted light received at other photosensitive locations on the ring-shaped photosensitive surface differ relatively significantly from the above and do not fall within the average optical path length range C. Since the average optical path length of the emitted light being within the average optical path length range C indicates that the emitted light has primarily passed through the dermis, emitted light that is not within the average light range C may not have primarily passed through the dermis. At the same time, because the annular photosensitive surface emits a single output light, if the skin tissue is non-uniform, the signal quality of the output light obtained from the annular photosensitive surface is not high, and furthermore, this affects measurement precision.

[0156] Meanwhile, non-circular photosensitive surfaces can be installed according to actual conditions. Taking the example described above as an example, if it is assumed that the average optical path length is within the average optical path length range D but not within the average optical path length range C, two non-circular photosensitive surfaces can be applied. Here, one non-circular photosensitive surface is intended to receive the light intensity value of the emitted light whose average optical path length is within the average optical path length range C, and the other non-circular photosensitive surface is intended to receive the light intensity value of the emitted light whose average optical path length is within the average optical path length range D. Since the output light intensity of the two non-circular photosensitive surfaces matches the actual value, it is advantageous for ensuring measurement precision.

[0157] Third, when measuring tissue components by applying a pulse wave-based time-difference measurement method, the difference between systolic and diastolic light intensity must be maximized, that is, to ensure sufficient utilization of the pulse signal. In the aforementioned case, since most of the annular photosensitive surface is not positioned over the blood vessel, it affects the pulse signal collection effect; therefore, the degree of difference between systolic and diastolic light intensity was reduced. From this, it can be seen that the degree of difference between systolic and diastolic light intensity obtained by applying an annular photosensitive surface is smaller than the degree of difference obtained by applying a non-annular photosensitive surface.

[0158] Fourth, due to the influence of tissue non-uniformity and physiological background variations on the emitted light, there may be a difference in the average optical path length of the emitted light received by different photosensitive surfaces having the same source detection distance from the center of the incident light. Therefore, tissue composition measurement can be performed by applying the output light intensities collected by different photosensitive surfaces having the same source detection distance from the center of the incident light and performing a difference operation. The aforementioned acyclic photosensitive surfaces can be implemented as follows. That is, for the same source detection distance, at least two acyclic photosensitive surfaces can be discretely installed around the center of the incident light to realize two output light intensities.

[0159] Fifth, the difficulty of the production process is relatively low, and the production cost is relatively low.

[0160] A fourth aspect is described below in conjunction with FIG. 5. FIG. 5 schematically illustrates a schematic diagram of a difference measurement according to an embodiment of the present disclosure. As shown in FIG. 5, FIG. 5 includes four fan-shaped ring photosensitive surfaces, each being fan-shaped ring photosensitive surface 1, fan-shaped ring photosensitive surface 2, fan-shaped ring photosensitive surface 3, and fan-shaped ring photosensitive surface 4. The four fan-shaped ring photosensitive surfaces are used individually, and each fan-shaped ring photosensitive surface has a corresponding output light intensity. The centers of the four fan-shaped ring photosensitive surfaces are at the same distance from the center of the incident light. That is, they have the same source detection distance. Because the average optical path length corresponding to the emitted light received by fan-shaped ring photosensitive surface 1 and fan-shaped ring photosensitive surface 2 differs due to tissue non-uniformity, a difference measurement can be implemented by performing a difference operation based on the output light intensity collected by fan-shaped ring photosensitive surface 1 and the output light intensity collected by fan-shaped ring photosensitive surface 2.

[0161] According to an embodiment of the present disclosure, a non-circular photosensitive surface includes a fan-shaped ring photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface.

[0162] According to an embodiment of the present disclosure, a polygonal photosensitive surface includes a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

[0163] According to an embodiment of the present disclosure, a corresponding fan-shaped ring photosensitive surface can be obtained by designing the centrifugal angle according to actual conditions. For example, a fan-shaped ring photosensitive surface with a centrifugal angle of 90°, a fan-shaped ring photosensitive surface with a centrifugal angle of 180°, and a fan-shaped ring photosensitive surface with a center angle of 45°.

[0164] According to an embodiment of the present disclosure, FIG. 6 schematically illustrates a schematic diagram of a ring-shaped photosensitive surface according to an embodiment of the present disclosure. FIG. 7 schematically illustrates a schematic diagram of a fan-shaped ring photosensitive surface according to an embodiment of the present disclosure. FIG. 8 schematically illustrates a schematic diagram of a circular photosensitive surface according to an embodiment of the present disclosure. FIG. 9 schematically illustrates a schematic diagram of a square photosensitive surface according to an embodiment of the present disclosure.

[0165] According to an embodiment of the present disclosure, a homogeneous photosensitive surface may include an annular photosensitive surface or a non-annular photosensitive surface. The homogeneous photosensitive surface includes one or a plurality of photosensitive surfaces. The homogeneous photosensitive surface is intended to output a single output light intensity.

[0166] According to an embodiment of the present disclosure, the photosensitive surfaces of the same type may be an annular photosensitive surface or a non-annular photosensitive surface. That is, the photosensitive surfaces of the same type appear as an annular photosensitive surface or a non-annular photosensitive surface overall. Depending on the number of photosensitive surfaces included in the photosensitive surfaces of the same type, it can be determined whether the overall shape is formed by a single photosensitive surface or by a combination of multiple photosensitive surfaces. Here, the shape of each photosensitive surface among the photosensitive surfaces of the same type may be an annular photosensitive surface or a non-annular photosensitive surface.

[0167] According to an embodiment of the present disclosure, a homogeneous photosensitive surface is a ring-shaped photosensitive surface. When the homogeneous photosensitive surface comprises one photosensitive surface, the homogeneous photosensitive surface is an independent ring-shaped photosensitive surface; when the homogeneous photosensitive surface comprises a plurality of photosensitive surfaces, the homogeneous photosensitive surface is a ring-shaped photosensitive surface formed by a combination of the plurality of photosensitive surfaces. When the homogeneous photosensitive surface is a non-ring-shaped photosensitive surface, when the homogeneous photosensitive surface comprises one photosensitive surface, the homogeneous photosensitive surface is an independent non-ring-shaped photosensitive surface; when the homogeneous photosensitive surface comprises a plurality of photosensitive surfaces, the homogeneous photosensitive surface is a non-ring-shaped photosensitive surface formed by a combination of the plurality of photosensitive surfaces.

[0168] According to an embodiment of the present disclosure, a plurality of photosensitive surfaces participating in the combination are arranged closely so that there is no gap between adjacent photosensitive surfaces. Currently, circular or rectangular photosensitive surfaces are relatively common, and the difficulty of the manufacturing process and the manufacturing cost are relatively low, whereas photosensitive surfaces of other shapes generally require custom manufacturing, and the difficulty of the manufacturing process and the manufacturing cost are relatively high. Therefore, if there is a limit on the manufacturing cost, a combination method can be applied to combine a plurality of circular photosensitive surfaces and / or a plurality of rectangular photosensitive surfaces to form a photosensitive surface of a different shape. Here, the rectangular includes a square or a rectangle.

[0169] In addition, the level of production cost incurred by a photosensitive surface is related to the size of the surface area; generally, the larger the surface area, the higher the production cost. If a relatively large photosensitive surface is required and multiple relatively small photosensitive surfaces currently exist, a relatively large photosensitive surface can be obtained by combining the multiple relatively small photosensitive surfaces to lower production costs.

[0170] According to an embodiment of the present disclosure, when it is determined that the distance of a like photosensitive surface from a target area is greater than or equal to a second distance limit, the like photosensitive surface includes a ring-shaped photosensitive surface, a fan-shaped ring photosensitive surface, a fan-shaped photosensitive surface, a circular photosensitive surface, or a square photosensitive surface.

[0171] According to an embodiment of the present disclosure, when the distance between a photosensitive surface of the same type and a target area is greater than or equal to a second distance limit, a photosensitive surface of an appropriate shape can be selected according to the shaking conditions of the actual emitted light to minimize the adverse effect of shaking on the measurement.

[0172] The target site may be the area where the tremor occurs. One of the sources causing the tremor is the pulse, and since the pulse is associated with blood vessels, the target site may be the blood vessels. Generally, the tremor distribution of emitted light near blood vessels has a constant directionality, whereas the tremor distribution of emitted light far from blood vessels is relatively uniform and lacks directionality.

[0173] If the photosensitive surfaces are located far from the target area (e.g., target blood vessel), the shake distribution of the emitted light may be relatively uniform; in this case, a ring-shaped photosensitive surface, a fan-shaped ring photosensitive surface, a circular photosensitive surface, or a square photosensitive surface may be selected. The fact that the photosensitive surfaces are located far from the target area can be understood as the distance from the target area of ​​each photosensitive surface among the photosensitive surfaces being greater than or equal to a second distance limit. The distance from the target area of ​​each photosensitive surface among the photosensitive surfaces being greater than or equal to the second distance limit may include the distance from the target area of ​​the edge of the photosensitive surface closest to the target area among the photosensitive surfaces being greater than or equal to the second distance limit, or the distance from the target area of ​​the center of the photosensitive surface closest to the target area among the photosensitive surfaces being greater than or equal to the second distance limit, where the photosensitive surface and the target area are not in contact, and the distance from the target area of ​​the center of the photosensitive surface closest to the target area among the photosensitive surfaces being greater than or equal to the second distance limit.

[0174] When like photosensitive surfaces are located far from the target area, if the average optical path length of the emitted light received at different exposure positions of each photosensitive surface among the like photosensitive surfaces is less than or equal to the optical path length limit, it is possible to reflect that the flickering of the emitted light is influenced by the size of the optical path length. Here, the larger the average optical path length of the emitted light, the more pronounced the flickering of the emitted light becomes, and conversely, the less pronounced the flickering of the emitted light becomes. In this case, the design can be configured so that the corresponding arc length becomes longer as the position moves further from the center of the incident light, thereby allowing for the selection of a ring-shaped photosensitive surface, a fan-shaped ring photosensitive surface, or a fan-shaped photosensitive surface.

[0175] If like photosensitive surfaces are located far from the target area, and the average optical path length of the emitted light received at different exposure positions of each photosensitive surface among the like photosensitive surfaces is greater than the optical path length limit, it can be reflected that the flickering of the emitted light is almost independent of the optical path length. In this case, a circular or square photosensitive surface can be selected.

[0176] According to an embodiment of the present disclosure, if the homogeneous photosensitive surface comprises a single photosensitive surface, the fan-shaped ring photosensitive surface is an independent fan-shaped ring photosensitive surface. If the homogeneous photosensitive surface comprises a plurality of photosensitive surfaces, the fan-shaped ring photosensitive surface is a photosensitive surface formed by a combination of the plurality of photosensitive surfaces. Likewise, if the homogeneous photosensitive surface comprises a ring-shaped photosensitive surface, a circular photosensitive surface, a square photosensitive surface, or a fan-shaped photosensitive surface, it may be an independently formed homogeneous photosensitive surface or a homogeneous photosensitive surface formed by a combination.

[0177] Currently, circular or rectangular photosensitive surfaces are relatively common, have a relatively low manufacturing difficulty, and have relatively low production costs. However, since photosensitive surfaces of other shapes generally require custom manufacturing, have a relatively high manufacturing difficulty, and have relatively high production costs, if there are limitations on production costs, it should be noted that if the distance of a photosensitive surface of the same type from the target area is greater than or equal to the second distance limit, the photosensitive surface of the same type includes a circular or rectangular photosensitive surface.

[0178] According to an embodiment of the present disclosure, when it is determined that the distance of a homogeneous photosensitive surface from a target area is less than or equal to a third distance limit, the shape of the homogeneous photosensitive surface is determined according to the area of ​​the flicker distribution shape of the emitted light.

[0179] According to an embodiment of the present disclosure, if the distance between a photosensitive surface and a target area is less than or equal to a third distance limit, the shape area of ​​the photosensitive surface is determined according to the flicker distribution of the emitted light.

[0180] According to an embodiment of the present disclosure, if the co-photosensitive surface is close to a target area (e.g., a target blood vessel), it may reflect that the ripple distribution of the emitted light has a certain directionality. In this case, the shape of the co-photosensitive surface may be determined according to the ripple distribution of the emitted light. Alternatively, the shape of the co-photosensitive surface is a shape similar to the ripple distribution of the emitted light. For example, if the ripple distribution of the emitted light is elliptical, the shape of the co-photosensitive surface may be designed as an elliptical photosensitive surface. For example, if the ripple distribution of the emitted light is rectangular, the shape of the co-photosensitive surface may be designed as a rectangular photosensitive surface. Or, if the ripple distribution of the emitted light is rhomboidal, the shape of the co-photosensitive surface may be designed as a rhomboidal photosensitive surface.

[0181] According to an embodiment of the present disclosure, the oscillation distribution of the emitted light can be decomposed into an oscillation distribution along a first direction and an oscillation 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 photosensitive surface along the first direction to the length of the photosensitive surface along the second direction is determined according to the ratio of the oscillation width of the emitted light along the first direction to the oscillation width of the emitted light along the second direction, and the oscillation width of the emitted light along the first direction is the largest.

[0182] According to the present disclosure, when the vibration distribution of the emitted light includes vibration distributions in two mutually perpendicular directions, the vibration distributions in two mutually perpendicular directions are obtained by decomposing the vibration of the emitted light into two mutually perpendicular directions, a first direction and a second direction, and these two mutually perpendicular directions are respectively referred to as the first direction and the second direction. In this case, if the vibration amplitude in the first direction of the emitted light is the largest, the ratio of the length of the photosensitive surface along the first direction and the length along the second direction is set according to the ratio of the vibration amplitude along the first direction and the second direction of the emitted light, so that the ratio of the length of the photosensitive surface along the first direction and the length along the second direction of the emitted light is greater than or equal to the ratio of the vibration amplitude along the first direction and the second direction of the emitted light.

[0183] For example, if the first direction and the second direction are the Y-axis and X-axis directions of a Cartesian coordinate system, respectively, the ratio of the flickering amplitude of the emitted light along the Y-axis direction to the flickering amplitude along the X-axis direction is It is represented as, and for homogeneous photosensitive surfaces, the ratio of the length along the Y-axis direction to the length along the X-axis direction If expressed as, It could be.

[0184] According to an embodiment of the present disclosure, the 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 is determined according to the ratio of the flicker width along the first direction of the emitted light to the flicker width along the second direction of the emitted light. The ratio of the major axis to the minor axis of the elliptical photosensitive surface is determined according to the ratio of the flicker width along the first direction of the emitted light to the flicker width along the second direction of the emitted light.

[0185] According to an embodiment of the present disclosure, if the distance between a co-photosensitive surface and a target area is less than or equal to a third distance limit, the flicker distribution of the emitted light can be decomposed into a flicker distribution along a first direction and a second direction, and the first direction and the second direction are perpendicular to each other, the co-photosensitive surface may include a rectangular photosensitive surface or an elliptical photosensitive surface. Here, the ratio of the length to the width of the rectangular photosensitive surface is greater than or equal to the ratio of the flicker width along the first direction of the emitted light to the flicker width 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 flicker width along the first direction of the emitted light to the flicker width along the second direction.

[0186] According to an embodiment of the present disclosure, each output light intensity is obtained by processing according to the light intensity value of the emitted light collected by one or more photosensitive surfaces, and specifically, may include the following operations.

[0187] When using a combination of one or more photosensitive surfaces to output a single output light intensity, or when using each of the one or more photosensitive surfaces individually, a calculation is performed on the light intensity value of the emitted light collected by each photosensitive surface to obtain a single output light intensity.

[0188] According to an embodiment of the present disclosure, a photosensitive surface for outputting a single output light intensity is referred to as a homogeneous photosensitive surface, and the homogeneous photosensitive surface may include one or a plurality of photosensitive surfaces. Here, the condition for combining different photosensitive surfaces may be that the average optical path length of the emitted light received by each photosensitive surface is within an average optical path length range. The average optical path length range may be a range configured to be greater than or equal to a first average optical path length limit and less than or equal to a second average optical path length limit. The first average optical path length limit and the second average optical path length limit may be determined based on the average optical path length and the range of variation in optical path length. The average optical path length is an average value obtained by calculating the average optical path length of the emitted light received at each photosensitive position of the homogeneous photosensitive surface.

[0189] A photosensitive surface is generally used in combination with an amplification circuit corresponding to it to output a single light intensity value. In order for a photosensitive surface of the same type to output a relatively accurate light intensity, the product of the photoresponse rate of each photosensitive surface of the same type and the amplification factor of the amplification circuit used in combination with that photosensitive surface must be a preset value. Furthermore, if it is ensured that the photoresponse rate of each photosensitive surface and the amplification factor of the amplification circuit used in combination with that photosensitive surface are identical preset values, the photosensitive surface of the same type is implemented to output a single light intensity. If there is a case where the product of the photoresponse rate of the photosensitive surface and the amplification factor of the amplification circuit used in combination with that photosensitive surface is not a preset value, a corresponding method must be applied to ensure that the product becomes an identical preset value.

[0190] It is possible to implement homogeneous photosensitive surfaces outputting a single output light intensity by applying a hardware or software method.

[0191] Method 1 is a hardware method. The cathodes of different photosensitive surfaces among the same photosensitive surfaces can be electrically connected to each other, and the anodes can be electrically connected to each other. That is, electrical connections between different photosensitive surfaces can be implemented as common cathodes and common anodes. In this case, it is equivalent to implementing the use of one or more photosensitive surfaces combined by arranging different photosensitive surfaces in parallel to output a single light intensity. It should be noted that a relatively accurate output light intensity must be obtained by ensuring that the photoresponse rates of the different photosensitive surfaces match as much as possible.

[0192] Method 2 is a software method. Among the same photosensitive surfaces, the cathodes are not connected to each other and the anodes are not connected to each other. That is, each photosensitive surface is used individually to output a single light intensity value. After obtaining the light intensity value corresponding to each photosensitive surface, a corresponding algorithm is applied to weighted sum the light intensity values ​​of each photosensitive surface among the same photosensitive surfaces to obtain a single output light intensity.

[0193] Alternatively, the output light intensity corresponding to the same photosensitive surface can be determined by the following formulas (2) and (3).

[0194] (2)

[0195] (3)

[0196] Here, I represents the output light intensity corresponding to the same photosensitive surface, and I i represents the light intensity value corresponding to photosensitive surface i, and and N represents the quantity of photosensitive surfaces included in the same photosensitive surface, and and, M represents the total quantity of photosensitive surfaces, and α i represents the weighting factor corresponding to photosensitive surface i, H represents a preset value, and β i represents the photoresponse rate corresponding to photosensitive surface i, and γ irepresents the amplification ratio of the amplification circuit used in combination with the photosensitive surface.

[0197] According to an embodiment of the present disclosure, the photosensitive surface is obtained after installing a mask on an initial photosensitive surface, and the light transmittance of the mask is less than or equal to the light transmittance limit.

[0198] According to an embodiment of the present disclosure, the shape of the mask is determined according to the shape of the flicker distribution of the emitted light.

[0199] According to an embodiment of the present disclosure, since circular or rectangular photosensitive surfaces are currently relatively common, have a relatively low difficulty in the manufacturing process, and have a relatively low manufacturing cost, and photosensitive surfaces of other shapes generally require custom manufacturing, have a relatively high difficulty in the manufacturing process, and have a relatively high manufacturing cost, a method of installing a mask on an initial photosensitive surface can be applied if there is a limit on the manufacturing cost. Here, it is difficult to receive light intensity values ​​in the parts covered by the mask on the initial photosensitive surface because the light transmittance of the mask is less than or equal to the light transmittance limit.

[0200] Based on the above description, it is possible to implement obtaining a photosensitive surface of a preset shape and area by installing the shape and position of the mask according to the actual required shape and area. Here, the actual required shape and area can be determined according to the flicker distribution of the emitted light.

[0201] For example, FIG. 10 schematically illustrates a schematic diagram of obtaining a photosensitive surface by installing a mask on an initial photosensitive surface according to an embodiment of the present disclosure. In FIG. 10, the initial photosensitive surface is a square photosensitive surface, and the photosensitive surface is a circular photosensitive surface.

[0202] According to an embodiment of the present disclosure, the intensity distribution of the light stain irradiated by incident light on a measurement area is uniform.

[0203] According to an embodiment of the present disclosure, in order to ensure better measurement precision by performing tissue component measurements on a subject under more relaxed requirements, a method can be implemented by ensuring that the intensity distribution of the optical spots irradiated by incident light onto the measurement area is uniform. At the same time, the more uniform the intensity distribution of the optical spots irradiated by incident light onto the measurement area, the lower the requirement for the reproducibility of controllable measurement conditions, and the better the effect of suppressing the influence of uncontrollable measurement conditions on the measurement results by applying a differential measurement method. Therefore, better measurement precision can be ensured. Furthermore, while the measure to make the intensity distribution of the optical spots of the incident light uniform in the measurement area attenuates the optical energy of the incident light to some extent, tissue component measurement requires that the optical energy of the incident light not be too low; therefore, the attenuation of the optical energy of the incident light should be as small as possible in a situation where the intensity distribution of the optical spots of the incident light is ensured to be as uniform as possible in the measurement area. Additionally, if the incident light is implemented using an optical fiber transmission method, the distribution of the optical spots of the incident light in the measurement area can be made uniform, and the adverse effect of optical fiber vibration on the measurement results can also be reduced.

[0204] According to an embodiment of the present disclosure, the area of ​​the light spot irradiated by incident light on the measurement area is greater than or equal to the light spot area limit.

[0205] According to an embodiment of the present disclosure, in order to ensure better measurement precision by allowing the subject to be measured to perform tissue component measurements under more relaxed requirements, a method can be implemented by applying a method in which the area of ​​the optical spot irradiated by incident light onto the measurement area is greater than or equal to the optical spot area limit. At the same time, within a certain range, the larger the area of ​​the optical spot irradiated by incident light onto the measurement area, the lower the requirement for the reproducibility of controllable measurement conditions, and the better the effect of suppressing the influence of uncontrollable measurement conditions on the measurement results by applying a differential measurement method. Therefore, measurement precision can be better ensured. Here, the optical spot area limit can be set according to actual conditions and is not specifically limited herein. Furthermore, if the incident light is implemented using an optical fiber transmission method, the area of ​​the optical spot irradiated by incident light onto the measurement area can be made greater than or equal to the optical spot area limit, and the adverse influence of optical fiber vibration on the measurement results can also be reduced.

[0206] FIG. 11 schematically shows a block diagram of a tissue component measuring device according to an embodiment of the present disclosure.

[0207] As illustrated in FIG. 11, the tissue component measuring device (1100) includes a light source module (1110), a collection module (1120), and a processing module (1130).

[0208] The light source module (1110) is intended to irradiate a measurement area with incident light of a plurality of preset wavelengths. Here, each incident light is emitted from at least one emission position after passing through the measurement area to form at least one emission light. The emission position of the incident light includes one.

[0209] The collection module (1120) includes M photosensitive surfaces, and each photosensitive surface can collect light intensity values ​​of emitted light emitted from an emission position within a preset anti-shake range corresponding to the photosensitive surface. The collection module (1120) is intended to obtain T output light intensities by acquiring light intensity values ​​corresponding to each emitted light collected by the M photosensitive surfaces. Each output light intensity is obtained by processing according to the light intensity values ​​of the emitted light collected by one or more of the photosensitive surfaces. am.

[0210] The processing module (1130) is for determining the concentration of a tissue component to be measured according to at least one output light intensity corresponding to a plurality of preset wavelengths.

[0211] According to the technical method of the embodiment of the present disclosure, the photosensitive surface can collect light intensity values ​​of emitted light emitted from an emission position within a corresponding preset anti-vibration range. Since the photosensitive surface having the above-described characteristics has improved the ratio of the area capable of stably receiving emitted light to the area of ​​the photosensitive surface, the stability of receiving emitted light has been improved, and furthermore, the adverse effect of changes in the intensity distribution of emitted light caused by vibration can be reduced, thereby improving measurement precision.

[0212] According to an embodiment of the present disclosure, the ratio of the average optical path length of the emitted light received by each photosensitive surface in the target tissue layer to the total optical path length, which is the total distance the emitted light is transmitted within the measurement area, is greater than or equal to a ratio limit.

[0213] According to an embodiment of the present disclosure, the total area of ​​the homogeneous photosensitive surface is determined according to the tissue structure characteristics within the measurement area. The homogeneous photosensitive surface comprises one or more photosensitive surfaces. The homogeneous photosensitive surface is intended to output a single output light intensity.

[0214] According to an embodiment of the present disclosure, the ratio of the area of ​​each photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to a ratio limit.

[0215] According to an embodiment of the present disclosure, the ratio limit is greater than or equal to 0.04 mm.

[0216] According to an embodiment of the present disclosure, the photosensitive surface and the surface of the measurement area are in contact or non-contact.

[0217] According to an embodiment of the present disclosure, the distance between the photosensitive surface and the surface of the measurement area is less than or equal to a first distance limit, and the efficiency of the photosensitive surface receiving the emitted light is greater than or equal to an efficiency limit.

[0218] According to an embodiment of the present disclosure, among the M photosensitive surfaces, there is one or more co-photosensitive surfaces corresponding to each preset wavelength. Here, the co-photosensitive surfaces are intended to collect a first output light intensity and / or a second output light intensity corresponding to the preset wavelength at different times. The first output light intensity is a systolic light intensity, and the second output light intensity is an diastolic light intensity. The co-photosensitive surfaces include one or more photosensitive surfaces. The processing module (1130) is intended to determine the concentration of the tissue component to be measured by the first output light intensity and the second output light intensity corresponding to each preset wavelength.

[0219] According to an embodiment of the present disclosure, among the M photosensitive surfaces, there is a first photosensitive surface and a second photosensitive surface corresponding to each preset wavelength. The first photosensitive surface is for outputting a first output light intensity corresponding to the preset wavelength, and the second photosensitive surface is for outputting a second output light intensity. The first photosensitive surface includes one or more photosensitive surfaces. The second photosensitive surface includes one or more photosensitive surfaces. The processing module (1130) is for determining the concentration of a tissue component to be measured according to the first output light intensity and the second output light intensity corresponding to each preset wavelength.

[0220] According to an embodiment of the present disclosure, the average optical path length of the emitted light received at different photosensitive positions of each photosensitive surface among the first similar photosensitive surfaces falls within a first average optical path length range. The first average optical path length range is determined according to the first average optical path length, which is an average value obtained by calculating the average optical path length of the emitted light received at each photosensitive position of the first similar photosensitive surface. The average optical path length of the emitted light received at different photosensitive positions of each photosensitive surface among the second similar photosensitive surfaces falls within a second average optical path length range. The second average optical path length range is determined according to the second average optical path length, which is an average value obtained by calculating the average optical path length of the emitted light received at each photosensitive position of the second similar photosensitive surface.

[0221] According to an embodiment of the present disclosure, the absolute value of the difference between the average value of the first optical path length and the average value of the second optical path length falls within the range of the difference between the first optical path lengths.

[0222] According to an embodiment of the present disclosure, the first average optical path length range is smaller than or equal to the first optical path length range, and the second average optical path length range is smaller than or equal to the first optical path length difference range.

[0223] According to an embodiment of the present disclosure, the first optical path length difference range is determined according to the optimal difference optical path length corresponding to a preset wavelength.

[0224] According to an embodiment of the present disclosure, the source detection distance of each photosensitive surface among the first photosensitive surfaces corresponding to a preset wavelength, which is located away from the center of the incident light, is within a preset source detection distance range corresponding to the preset wavelength. The preset source detection distance range is determined according to the source detection distance of the flow reference position corresponding to the preset wavelength, which is located away from the center of the incident light.

[0225] According to an embodiment of the present disclosure, among the M photosensitive surfaces, there exists a photosensitive surface corresponding to each preset wavelength. The photosensitive surface is intended to collect a third output light intensity corresponding to a preset wavelength. The photosensitive surface includes one or a plurality of photosensitive surfaces. The processing module (1130) is intended to obtain at least one difference signal by differential processing the third output light intensity corresponding to different preset wavelengths, and to determine the concentration of the tissue component to be measured according to the at least one difference signal.

[0226] According to an embodiment of the present disclosure, the processing module (1130) obtains a difference signal by performing difference processing on a first output light intensity and a second output light intensity corresponding to a preset wavelength, obtains at least one wavelength difference signal by directly performing difference processing on difference signals corresponding to different preset wavelengths, and determines the concentration of a tissue component to be measured according to at least one wavelength difference signal.

[0227] According to an embodiment of the present disclosure, among the M photosensitive surfaces, there is a photosensitive surface corresponding to each preset wavelength. The photosensitive surface is intended to collect a fourth output light intensity corresponding to the preset wavelength. The photosensitive surface includes one or more photosensitive surfaces. The processing module (1130) is intended to determine the concentration of the tissue component to be measured according to the fourth output light intensity corresponding to each preset wavelength.

[0228] According to an embodiment of the present disclosure, the difference between the average optical path length of the emitted light received at different photosensitive positions of each photosensitive surface among like photosensitive surfaces and the optimal optical path length corresponding to a preset wavelength falls within a second optical path length difference range.

[0229] According to an embodiment of the present disclosure, each photosensitive surface includes an annular photosensitive surface or a non-annular photosensitive surface, and the shapes of the different photosensitive surfaces are the same or different.

[0230] According to an embodiment of the present disclosure, a non-circular photosensitive surface includes a fan-shaped ring photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface.

[0231] According to an embodiment of the present disclosure, a polygonal photosensitive surface includes a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

[0232] According to an embodiment of the present disclosure, a co-photosensitive surface may include an annular photosensitive surface or a non-annular photosensitive surface. A co-photosensitive surface includes one or a plurality of photosensitive surfaces. A co-photosensitive surface is intended to output a single output light intensity.

[0233] According to an embodiment of the present disclosure, the photosensitive surface of the same type is a ring-shaped photosensitive surface, wherein when the photosensitive surface of the same type comprises one photosensitive surface, the photosensitive surface of the same type is an independent ring-shaped photosensitive surface; and when the photosensitive surface of the same type comprises a plurality of photosensitive surfaces, the photosensitive surface of the same type is a ring-shaped photosensitive surface formed by a combination of a plurality of photosensitive surfaces. The photosensitive surface of the same type is a non-ring-shaped photosensitive surface, wherein when the photosensitive surface of the same type comprises one photosensitive surface, the photosensitive surface of the same type is an independent non-ring-shaped photosensitive surface; and when the photosensitive surface of the same type comprises a plurality of photosensitive surfaces, the photosensitive surface of the same type is a non-ring-shaped photosensitive surface formed by a combination of a plurality of photosensitive surfaces.

[0234] According to an embodiment of the present disclosure, when it is determined that the distance of a like photosensitive surface from a target area is greater than or equal to a second distance limit, the like photosensitive surface includes a ring-shaped photosensitive surface, a fan-shaped ring photosensitive surface, a fan-shaped photosensitive surface, a circular photosensitive surface, or a square photosensitive surface.

[0235] According to an embodiment of the present disclosure, when it is determined that the distance between a homogeneous photosensitive surface and a target area is less than or equal to a third distance limit, the shape of the homogeneous photosensitive surface is determined according to the flicker distribution of the emitted light.

[0236] According to an embodiment of the present disclosure, the oscillation distribution of the emitted light can be decomposed into an oscillation distribution along a first direction and an oscillation distribution along a second direction. The first direction and the second direction are perpendicular to each other. The ratio of the length of the photosensitive surface along the first direction to the length of the photosensitive surface along the second direction is determined by the ratio of the oscillation width of the emitted light along the first direction to the oscillation width of the emitted light along the second direction, and the oscillation width of the emitted light along the first direction is the largest.

[0237] According to an embodiment of the present disclosure, the photosensitive surface comprises a rectangular photosensitive surface or an elliptical photosensitive surface, wherein the ratio of the length to the width of the rectangular photosensitive surface is determined according to the ratio of the oscillation width along the first direction of the emitted light to the oscillation width along the second direction of the emitted light, and the ratio of the major axis to the minor axis of the elliptical photosensitive surface is determined according to the ratio of the oscillation width along the first direction of the emitted light to the oscillation width along the second direction of the emitted light.

[0238] According to an embodiment of the present disclosure, the anodes of different photosensitive surfaces among M photosensitive surfaces are not electrically connected to each other, some photosensitive surfaces are electrically connected, or all photosensitive surfaces are electrically connected.

[0239] According to an embodiment of the present disclosure, each of the M photosensitive surfaces can be used alone. In this case, the positive terminals of different photosensitive surfaces among the M photosensitive surfaces are not electrically connected.

[0240] Some of the M photosensitive surfaces can be combined for use. In this case, the anodes of the different photosensitive surfaces used in combination can be electrically connected.

[0241] All of the M photosensitive surfaces can be combined and used. In this case, the anodes of the different photosensitive surfaces used in combination can be electrically connected.

[0242] According to an embodiment of the present disclosure, FIG. 12 schematically illustrates a schematic diagram of the electrical connection of the anodes of different photosensitive surfaces according to an embodiment of the present disclosure. As shown in FIG. 12, the anodes of all photosensitive surfaces are electrically connected.

[0243] According to an embodiment of the present disclosure, different parts of the same photosensitive surface are on the same plane or different planes.

[0244] According to an embodiment of the present disclosure, the photosensitive surface may be a planar photosensitive surface or a three-dimensional photosensitive surface. Here, if all other parts of the photosensitive surface are on the same plane, the photosensitive surface is a planar photosensitive surface. If different parts of the photosensitive surface are on different planes, the photosensitive surface is a three-dimensional photosensitive surface. Specifically, whether a planar photosensitive surface or a three-dimensional photosensitive surface is applied can be determined according to the actual situation and is not specifically limited herein.

[0245] Alternatively, for contact measurements, to improve measurement precision, the contact between the target surface of the photosensitive surface and the skin surface of the measurement area should be maintained in a relatively good state. Here, the target surface of the photosensitive surface refers to the surface close to the measurement area. Since the flatness of the skin surface of the measurement area may not be high, applying a flat photosensitive surface may make it difficult to achieve a relatively good state of contact between the target surface of the photosensitive surface and the skin surface of the measurement area. On the other hand, since a stereoscopic photosensitive surface is one in which different parts lie on different planes, a stereoscopic photosensitive surface can be applied, and a specific type of stereoscopic photosensitive surface can be installed according to the tissue structure characteristics of the measurement area.

[0246] FIG. 13 schematically illustrates a schematic diagram of a stereoscopic photosensitive surface in the form of a glove according to an embodiment of the present disclosure. FIG. 14 schematically illustrates a schematic diagram of another stereoscopic photosensitive surface in the form of a glove according to an embodiment of the present disclosure.

[0247] FIG. 15 schematically illustrates a schematic diagram of a bracelet-type stereophotosensitive surface according to an embodiment of the present disclosure. FIG. 16 schematically illustrates another bracelet-type stereophotosensitive surface according to an embodiment of the present disclosure.

[0248] FIG. 17 schematically illustrates a schematic diagram of a stereoscopic photosensitive surface for measuring an arm according to an embodiment of the present disclosure. In FIG. 17, different parts of the photosensitive surface may be spaced apart from a preset plane depending on the tissue structure characteristics of the arm. In FIG. 17, h1 and h2 represent the distances between different parts of the photosensitive surface from a preset plane.

[0249] According to an embodiment of the present disclosure, a set of photosensitive surfaces comprising a plurality of photosensitive surfaces is in the same plane or in different planes.

[0250] According to an embodiment of the present disclosure, each photosensitive surface included in a set of photosensitive surfaces may be a planar photosensitive surface or a three-dimensional photosensitive surface. When a set of photosensitive surfaces includes a plurality of planar photosensitive surfaces, the form of the photosensitive surface represented by the set of photosensitive surfaces is realized as a three-dimensional photosensitive surface by applying a method of installing some or all of the planar photosensitive surfaces among the plurality of planar photosensitive surfaces on different planes.

[0251] Depending on the three-dimensional photosensitive surface formed by multiple planar photosensitive surfaces, the effect of the contact-type measurement described above may also be realized, which is not explained again here.

[0252] According to an embodiment of the present disclosure, the tissue component measuring device (1100) further comprises a mask installed on an initial photosensitive surface and having a light transmittance less than or equal to a light transmittance limit. The mask is intended to obtain a photosensitive surface after the mask is installed on the initial photosensitive surface.

[0253] According to an embodiment of the present disclosure, the shape of the mask is determined according to the shape of the flicker distribution of the emitted light.

[0254] As illustrated in FIG. 18, according to an embodiment of the present disclosure, the tissue component measuring device (1100) further comprises a measuring probe having M photosensitive surfaces and a first sleeve (1140) installed thereon. A first cross-section representing a cross-section of the first sleeve (1140) near the measuring area extends beyond the target surface of the measuring probe representing a surface near the measuring area.

[0255] According to an embodiment of the present disclosure, a first sleeve (1140) may be installed on a measuring probe to shield external light, such that the cross-section of the first sleeve (1140) near the measuring area extends beyond the target surface of the measuring probe. The external light may include surface reflected light and / or diffracted light.

[0256] According to an embodiment of the present disclosure, a scattering material is installed in a second cross section and / or an internal region of a first sleeve, wherein the first cross section and the second cross section are two cross sections facing each other, and the internal region includes a part of the internal region or the entire internal region.

[0257] According to an embodiment of the present disclosure, a method of installing a scattering material in a corresponding portion of the first sleeve (1140) can be applied to ensure that the intensity distribution of the light stain irradiated by incident light on the measurement area is uniform. The scattering material may include sulfuric acid, silica gel, or a target mixture, wherein the target mixture may include a mixture of polydimethylsiloxane and titanium dioxide particles.

[0258] As illustrated in FIG. 19, according to an embodiment of the present disclosure, the tissue component measuring device (1100) further comprises a second sleeve (1150) installed outside the target area of ​​the first sleeve (1140), wherein the target area represents a part or the entire area of ​​the first sleeve (1140) that extends beyond the target surface of the measuring probe.

[0259] According to an embodiment of the present disclosure, a method of installing a second sleeve (1150) outside the target area of ​​the first sleeve (1140) can be applied to make the light spot irradiated by incident light on the measurement area as large as possible.

[0260] According to an embodiment of the present disclosure, a scattering material is installed in the second sleeve (1150).

[0261] According to an embodiment of the present disclosure, if a second sleeve (1150) is installed, a method of installing a scatterer in a corresponding part of the second sleeve (1150) can be applied to make the intensity distribution of the light stain irradiated by incident light onto the measurement area uniform.

[0262] According to an embodiment of the present disclosure, the inner diameter of the first sleeve (1140) is greater than or equal to the inner diameter limit.

[0263] According to an embodiment of the present disclosure, the hole in the first section of the first sleeve (1140) is larger than or equal to the hole in the second section of the first sleeve (1140).

[0264] According to an embodiment of the present disclosure, in order to maximize the light spot irradiated by incident light onto the measurement area, a method may be applied in which the inner diameter of the first sleeve (1140) is greater than or equal to the inner diameter limit, and / or a method may be applied in which the hole in the first cross-section of the first sleeve (1140) is greater than or equal to the hole in the second cross-section of the first sleeve (1140). That is, the hole in the cross-section of the first sleeve (1140) closer to the measurement area is made greater than or equal to the hole in the cross-section of the first sleeve (1140) farther from the measurement area.

[0265] As illustrated in FIGS. 21 and 22, according to an embodiment of the present disclosure, a refractive index matching material is filled between the photosensitive surface and the measurement area.

[0266] According to an embodiment of the present disclosure, since vibration can destabilize the surface of the measurement area and further change the emission angle of the emitted light, in order to suppress adverse effects caused by vibration as much as possible, a refractive index matching material can be filled between the photosensitive surface and the measurement area to improve the stability and efficiency of the emitted light received by the photosensitive surface.

[0267] For example, the shaking caused by a pulse beat is used as an example. A pulse beat can be reflected through the state of the blood vessels. FIG. 20 schematically illustrates a schematic diagram of a photosensitive surface receiving emitted light when the refractive index matching material according to an embodiment of the present disclosure is not filled. In FIG. 20, blood vessel state 1 represents a vasoconstriction state, blood vessel state 2 represents a vasodilation state, skin state 1 represents a skin state corresponding to blood vessel state 1, and skin state 2 represents a skin state corresponding to blood vessel state 2. In FIG. 20, it can be seen that shaking can destabilize the skin surface of the measurement area and further change the angle of emission of the emitted light.

[0268] FIG. 21 schematically illustrates a schematic diagram of a photosensitive surface receiving emitted light when filled with a refractive index matching material according to an embodiment of the present disclosure.

[0269] FIG. 22 schematically illustrates another schematic diagram of a photosensitive surface receiving emitted light when filled with a refractive index matching material according to an embodiment of the present disclosure.

[0270] As shown in FIGS. 21 and 22, if a refractive index matching material is filled between the photosensitive surface and the measurement area, the stability and efficiency of the emitted light received by the measurement probe can be improved.

[0271] According to an embodiment of the present disclosure, the shape of the incident light includes a point, a linear, or a planar shape.

[0272] According to an embodiment of the present disclosure, the surface may include a circular, ring-shaped, square, or triangular shape.

[0273] According to an embodiment of the present disclosure, the positional relationship between an incident position and M photosensitive surfaces comprises one of the following: the positions of the M photosensitive surfaces are located inside the incident position; the positions of the M photosensitive surfaces are located outside the incident position; or the positions of the M photosensitive surfaces form an inclusive positional relationship with each incident position.

[0274] According to an embodiment of the present disclosure, the positional relationship between the incident position and M photosensitive surfaces may include one of the following situations and is described in conjunction with the drawings.

[0275] First, all M photosensitive surfaces are arranged around the outer periphery of the incident position. The positional relationship installation method described above forms an implementation method in which incident light is incident on the center and light is received at the outer edge. Refer to FIGS. 23 to 28. Here, FIGS. 23 to 26 are for the case of a single photosensitive surface, and FIGS. 27 to 28 are for the case of multiple photosensitive surfaces.

[0276] FIG. 23 schematically illustrates a schematic diagram according to an embodiment of the present disclosure in which a circular incident light is incident on the center and received by a ring-shaped photosensitive surface at the outer edge. FIG. 24 schematically illustrates a schematic diagram according to an embodiment of the present disclosure in which a ring-shaped incident light is incident on the center and received by a ring-shaped photosensitive surface at the outer edge. FIG. 25 schematically illustrates a schematic diagram according to an embodiment of the present disclosure in which a circular incident light is incident on the center and received by a fan-shaped ring photosensitive surface at the outer edge. FIG. 26 schematically illustrates a schematic diagram according to an embodiment of the present disclosure in which a circular incident light is incident on the center and received by a circular photosensitive surface at the outer edge.

[0277] FIG. 27 schematically illustrates a schematic diagram according to an embodiment of the present disclosure in which a circular incident light is incident on the center and two ring-shaped photosensitive surfaces receive it from the outside. FIG. 28 schematically illustrates a schematic diagram according to an embodiment of the present disclosure in which a circular incident light is incident on the center and two fan-shaped ring photosensitive surfaces receive it from the outside.

[0278] Second, the incident position is installed around the outer periphery of M photosensitive surfaces. That is, M photosensitive surfaces are surrounded by the incident position. The above-described positional relationship installation method forms an implementation method in which light is incident on the outer edge and received in the center. Refer to FIGS. 29 to 34. Here, FIGS. 29 to 31 represent the case of a single photosensitive surface, and FIGS. 32 to 34 represent the case of multiple photosensitive surfaces.

[0279] FIG. 29 schematically illustrates a schematic diagram according to an embodiment of the present disclosure in which a ring-shaped incident light is incident on the outer surface and a circular photosensitive surface receives it from the inside. FIG. 30 schematically illustrates a schematic diagram according to an embodiment of the present disclosure in which a fan-shaped ring incident light is incident on the outer surface and a circular photosensitive surface receives it from the inside. FIG. 31 schematically illustrates a schematic diagram according to an embodiment of the present disclosure in which a circular incident light is incident on the outer surface and a circular photosensitive surface receives it from the inside.

[0280] FIG. 32 schematically illustrates a first set of photosensitive surfaces including two annular photosensitive surfaces receiving an incident ring-shaped light source on the outer surface according to an embodiment of the present disclosure. FIG. 33 schematically illustrates a second set of photosensitive surfaces including one annular photosensitive surface and one circular photosensitive surface receiving an incident ring-shaped light source on the outer surface according to an embodiment of the present disclosure. FIG. 34 schematically illustrates a third set of photosensitive surfaces including four fan-shaped ring photosensitive surfaces receiving an incident ring-shaped light source on the outer surface according to an embodiment of the present disclosure.

[0281] Third, among the M photosensitive surfaces, W photosensitive surfaces are installed around the outside of the incident position, and MW photosensitive surfaces among the M photosensitive surfaces are installed inside the incident position. That is, W photosensitive surfaces are installed around the outside of the incident position, and MW photosensitive surfaces are surrounded by the incident position. The above-described positional relationship installation method forms an implementation method for receiving from both sides. Refer to FIG. 35. FIG. 35 schematically illustrates a schematic diagram of receiving from both sides according to an embodiment of the present disclosure.

[0282] According to an embodiment of the present disclosure, the tissue component measuring device (1100) further includes a protective member. The protective member is installed on the target surface of a photosensitive surface representing a surface close to the measurement area and is intended to protect the photosensitive surface.

[0283] According to an embodiment of the present disclosure, a protective layer may be installed on a target surface of a photosensitive surface to protect the photosensitive surface. The material used to manufacture the protective layer may be a transparent and flexible material. The protective layer may include a opaque film or optical glass. The distance between the protective layer and the target surface of the photosensitive surface may be determined by the material of the protective layer.

[0284] For example, if the protective layer is a opaque film, the distance between the opaque film and the target surface of the photosensitive layer may be 0. Also, if the protective layer is optical glass, the distance between the optical glass and the target surface of the photosensitive layer is greater than or equal to a distance limit. The distance limit can be set according to actual conditions.

[0285] Any plurality of modules or units according to embodiments of the present disclosure, or at least some functions of any plurality thereof, may be implemented in a single module. Any one or a plurality of modules or units according to embodiments of the present disclosure may be implemented by dividing them into a plurality of modules. Any one or a plurality of modules or units according to embodiments of the present disclosure may be implemented at least partially as hardware circuits such as, for example, a Field Programmable Gate Array (FPGA), Programmable Logic Arrays (PLA), System-on-Chip, a system on a substrate, a system on a package, or an Application Specific Integrated Circuit (ASIC); or may be implemented as hardware or firmware in other reasonable ways of integrating or packaging circuits; or may be implemented as any one of the three implementation methods of software, hardware, and firmware, or any suitable combination of some of these. Alternatively, one or a plurality of modules or units according to embodiments of the present disclosure may be implemented at least partially as computer program modules and may perform corresponding functions when said computer program modules are executed.

[0286] For example, any multiple of the collection module and processing module may be combined and implemented in a single module / unit, or any one of the modules / units may be divided into multiple modules. Additionally, at least some functions of one or more of these modules / units may be combined with at least some functions of other modules / units and implemented in a single module / unit. According to embodiments of the present disclosure, any one of the collection module and processing module may be at least partially implemented as a hardware circuit, such as, for example, a field programmable gate array (FPGA), a programmable logic array (PLA), a system-on-chip, a system on a board, a system on a package, or an application-specific integrated circuit (ASIC); or may be implemented as hardware or firmware, such as other reasonable methods of integrating or packaging the circuit; or may be implemented as any one of the three implementation methods of software, hardware, and firmware, or any suitable combination of several of these. Alternatively, at least one of the collection module and processing module may be at least partially implemented as a computer program module, and may perform a corresponding function when said computer program module is executed.

[0287] It should be noted that the tissue component measuring device and the tissue component measuring method in the embodiments of the present disclosure correspond in part to each other, and since the description of the tissue component measuring device part specifically refers to the tissue component measuring method part, it is not described again here.

[0288] FIG. 36 schematically illustrates a schematic diagram of a wearable device according to an embodiment of the present disclosure. The wearable device (3600) shown in FIG. 36 is merely an example and should not be limited in any way to the function and scope of use of the embodiment of the present disclosure.

[0289] As illustrated in FIG. 36, the wearable device (3600) includes a tissue component measuring device (1100).

[0290] According to the technical method of the embodiment of the present disclosure, the photosensitive surface can collect light intensity values ​​of emitted light emitted from an emission position within a corresponding preset anti-vibration range. Since the photosensitive surface having the above-described characteristics has improved the ratio of the area capable of stably receiving emitted light from the photosensitive surface to the area of ​​the photosensitive surface, the stability of receiving emitted light has been improved, and furthermore, the adverse effect of changes in the intensity distribution of emitted light caused by vibration can be reduced, thereby improving measurement precision.

[0291] As illustrated in FIG. 37, according to an embodiment of the present disclosure, the wearable device (3600) further includes a latching portion (3610) and a main body (3620). The latching portion (3610) and the main body (3620) are intended to implement the fixation of the tissue component measuring device (1100).

[0292] According to an embodiment of the present disclosure, FIG. 37 schematically illustrates a schematic diagram of an assembly process of a wearable device according to an embodiment of the present disclosure.

[0293] According to an embodiment of the present disclosure, since the mass of the wearable device (3600) is less than or equal to the mass limit, the movement law of the wearable device (3600) and the skin shaking law of the measurement area are matched.

[0294] According to an embodiment of the present disclosure, in order to improve measurement precision, the mass of the wearable device (3600) is made relatively light so that when the wearable device (3600) is worn at a position corresponding to the measurement area, it is possible to follow the skin vibration of the measurement area. That is, the law of movement of the wearable device (3600) and the law of skin vibration of the measurement area can be maintained in alignment. Therefore, the average optical path length of the emitted light received by the measurement probe can be maintained within a preset optical path length range during the skin vibration process. The reason why it is possible to implement that the average optical path length of the emitted light received by the measurement probe is maintained within a preset optical path length range during the skin vibration process of the measurement area as described above is that if the wearable device (3600) can follow the skin vibration of the measurement area, the relative position of the measurement probe in the measurement area does not change or essentially does not change. Therefore, the measurement probe can receive the emitted light emitted from a fixed emission position. The fixed emission position referred to here indicates an emission position where the relative position with respect to the measurement area does not change or essentially does not change. At the same time, during the skin shaking process in the measurement area, the relative position of the incident position of the incident light in the measurement area can be maintained without changing or essentially remaining unchanged. Therefore, when the incident position of the incident light and the exit position of the exit light are determined, it is possible to ensure that the average optical path length of the exit light remains as unchanged as possible.

[0295] For example, FIG. 38 schematically illustrates a schematic diagram in which, when the wearable device according to an embodiment of the present disclosure matches the skin shaking law, the average optical path length of the emitted light received by the measurement probe is maintained within a preset optical path length range during the skin shaking process. During the skin shaking process, the measurement probe (not shown in FIG. 38) can stably receive the incident light emitted from incident position B of the measurement area after the incident light enters incident position A of the measurement area. The range of movement of the skin is denoted as ξ1, and the range of movement of the measurement probe is denoted as ξ2, where ξ1=ξ2.

[0296] According to an embodiment of the present disclosure, the wearable device (3600) makes the range of movement of the skin in the measurement area smaller than or equal to the range of movement limit.

[0297] According to an embodiment of the present disclosure, in order to improve measurement precision, the mass of the wearable device (3600) is made relatively large so that when the wearable device (3600) is installed at a position corresponding to the measurement area, the skin shaking of the measurement area can be suppressed. That is, the range of movement of the skin in the measurement area is made smaller than or equal to the range of movement limit. Accordingly, the average optical path length of the emitted light received by the measurement probe is maintained within a preset range of optical path length during the skin shaking process. The reason why it is possible to implement the average optical path length of the emitted light received by the measurement probe being maintained within a preset range of optical path length during the skin shaking process of the measurement area as described above is that if the wearable device (3600) can suppress the skin shaking of the measurement area, the relative position of the measurement probe in the measurement area can be ensured not to change or to change fundamentally. Therefore, the measurement probe can receive the emitted light emitted from a fixed emission position. At the same time, since the relative position of the incident position of the incident light in the measurement area can be maintained unchanged or fundamentally unchanged during the skin shaking process in the measurement area, when the incident position of the incident light and the exit position of the exit light are determined, it is possible to ensure that the average optical path length of the exit light does not change.

[0298] For example, FIG. 39 schematically illustrates a schematic diagram in which, when a wearable device according to an embodiment of the present disclosure makes the width of skin movement in a measurement area smaller than or equal to a width limit, the average optical path length of the emitted light received by the measurement probe is maintained within a preset optical path length range during the skin shaking process. In FIG. 39, the width of skin movement in the measurement area is close to 0.

[0299] According to an embodiment of the present disclosure, a specific description of a tissue component measuring device may be referenced in the corresponding section above and is not described in detail here. Additionally, the tissue component measuring device includes a processor capable of performing various appropriate operations and processing according to a program stored in a Read-Only Memory (ROM) or a program loaded into Random Access Memory (RAM) from a storage unit. The processor may include, for example, a general-purpose microprocessor (e.g., CPU), an instruction set processor and / or a related chipset and / or a dedicated microprocessor (e.g., a dedicated integrated circuit (ASIC)). The processor may also include onboard memory for cache purposes. The processor may include a single processing unit or a plurality of processing units for performing other operations of the method flow according to an embodiment of the present disclosure.

[0300] Various programs and data necessary for the operation of the tissue component measuring device are stored in the RAM. The processor, ROM, and RAM are connected to each other via a bus. The processor performs various operations of the method flow according to the embodiments of the present disclosure by executing a program in the ROM and / or RAM. It should be noted that the program may be stored in one or more memories other than the ROM and RAM. The processor may also perform various operations of the method flow according to the embodiments of the present disclosure by executing a program stored in the one or more memories.

[0301] According to an embodiment of the present disclosure, a wearable device may also include an input / output (I / O) interface, and the input / output (I / O) interface may also be connected to a bus. The wearable device may further include one or more of the following components: an input unit including a keyboard, a mouse, etc. connected to the I / O interface; an output unit such as a cathode ray tube (CRT), a liquid crystal display (LCD), etc., and a speaker, etc.; a storage unit including a hard disk, etc.; and a communication unit including a network interface card such as a LAN card, a modem, etc. The communication unit performs communication processing through a network such as the Internet. A drive is also connected to the I / O interface as needed. A removable medium, such as a magnetic disk, an optical disk, a magneto-optical disk, a semiconductor memory, etc., is installed in the drive as needed so that a computer program read therefrom is installed in the storage portion as needed.

[0302] The present disclosure also provides a computer-readable storage medium that may be included in the device / device / system described in the above-described embodiments, or may exist independently without being assembled into said device / device / system. The above-described computer-readable storage medium carries one or more programs and implements a method according to an embodiment of the present disclosure when the above-described one or more programs are executed.

[0303] According to embodiments of the present disclosure, a computer-readable storage medium may be a non-volatile computer-readable storage medium. Examples may include, but are not limited to, a portable computer disk, a hard disk, random access memory (RAM), read-only memory (ROM), eraseable programmable read-only memory (EPROM or flash memory), portable compact disk read-only memory (CD-ROM), optical memory, magnetic memory, or any suitable combination of the above. In the present disclosure, a computer-readable storage medium may be any type of medium that includes or stores a program used for or in combination with the execution of a system, device, or element by instruction.

[0304] For example, according to an embodiment of the present disclosure, a computer-readable storage medium may include one or more memories other than the ROM and / or RAM described above, and / or ROM and RAM.

[0305] Embodiments of the present disclosure also include a computer program product comprising a computer program including program code for performing the method provided by the embodiments of the present disclosure.

[0306] When the computer program is executed by a processor, it performs the above-mentioned function limited to the system / device of the embodiment of the present disclosure. According to the embodiment of the present disclosure, the system, device, module, unit, etc. described above can be implemented through a computer program module.

[0307] In one embodiment, the computer program may rely on a tangible storage medium, such as an optical memory device or a magnetic memory device. In another embodiment, the computer program may be transmitted and allocated in the form of a signal on a network medium, downloaded and installed via a communication unit, and / or installed from a removable medium. The program code included in the computer program may be transmitted to any suitable network medium, including but not limited to wireless, wired, or any suitable combination of the above.

[0308] According to embodiments of the present disclosure, program code for executing a computer program provided in the embodiments of the present disclosure may be written in any combination of one or more programming languages, and specifically, such computational program may be executed using an advanced process and / or object-oriented programming language and / or assembly / machine language. Programming languages ​​include, but are not limited to, Java, C++, Python, the 'C' language, or similar programming languages. The program code may be executed entirely on a user's computing device, partially on a user's device, partially on a remote computing device, or entirely on a remote computing device or server. Where remote computing equipment is involved, the remote computing equipment may be connected to the user's computing device or to external computing equipment (e.g., connected via the Internet using an Internet service provider) through any type of network including a Local Area Network (LAN) or a Wide Area Network (WAN).

[0309] The flowcharts and block diagrams in the drawings illustrate implementable system architectures, functions, and operations of systems, methods, and computer program products according to various embodiments of the present disclosure. In this regard, each block in the flowchart or block diagram may represent a module, program segment, or part of code, and the aforementioned module, program segment, or part of code may include one or more executable instructions for implementing a defined logical function. It should also be noted that in some alternative implementations, the functions depicted in the blocks may occur differently from the order depicted in the drawings. For example, two consecutively shown blocks may actually be executed in nearly parallel, and sometimes in the reverse order, which is determined by the relevant function. It should also be noted that each block in the block diagram or flowchart, and combinations of blocks in the block diagram or flowchart, may be implemented as a dedicated hardware-based system for performing the defined function or operation, or as a combination of dedicated hardware and computer instructions. Those skilled in the art will understand that even if such combinations or combinations are not explicitly described in the present disclosure, multiple combinations and / or combinations of features described in the various embodiments and / or claims of the present disclosure may be made. In particular, without departing from the concept and intent of the present disclosure, multiple features described in each embodiment and / or claim of the present disclosure may be combined and / or combined. All such combinations and / or combinations are within the scope of the present disclosure.

[0310] The embodiments of the present disclosure have been described above. However, these embodiments are for illustrative purposes only and are not intended to limit the scope of the present disclosure. Although each embodiment has been described separately above, this does not mean that the measures of each embodiment cannot be advantageously combined. The scope of the present disclosure is limited by the appended claims and their equivalents. Without departing from the scope of the present disclosure, those skilled in the art may make various substitutions and modifications, and such substitutions and modifications shall be included within the scope of the present disclosure.

Claims

Claim 1 A method for measuring tissue composition performed by measuring tissue composition, comprising: irradiating a measurement area with incident light of a plurality of preset wavelengths - wherein each of the incident light is emitted from at least one emission position after passing through the measurement area to form at least one emission light, and the emission position of the incident light includes one -; obtaining light intensity values ​​corresponding to each of the emission light collected by M photosensitive surfaces to obtain T output light intensities - wherein each of the output light intensities is obtained by processing according to the light intensity value of the emission light collected by one or more of the photosensitive surfaces, and each of the photosensitive surfaces can collect the light intensity value of the emission light emitted from an emission position within a preset anti-shake range corresponding to the photosensitive surface, and 1 ≤ T ≤ M -; A method for measuring tissue components, comprising determining the concentration of a tissue component to be measured according to at least one output light intensity corresponding to a plurality of preset wavelengths, wherein the ratio of the area of ​​each photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to a ratio limit, said ratio limit is greater than or equal to 0.04 mm, the edge portion represents the perimeter length, and the non-edge portion represents the area, and the ratio in which the average light path length of the emitted light received by the photosensitive surface within the target tissue layer occupies the total light path length is greater than or equal to a ratio limit, or, the total area of ​​the same photosensitive surfaces is determined according to the tissue structure characteristics within the measurement area, said total light path length is the total distance the emitted light is transmitted within the measurement area, said same photosensitive surfaces include at least one photosensitive surface, and said same photosensitive surfaces are intended to output one output light intensity. Claim 2 A method for measuring tissue components according to claim 1, wherein the distance of the photosensitive surface from the surface of the measurement area is less than or equal to a first distance limit, and the efficiency of the photosensitive surface receiving emitted light is greater than or equal to an efficiency limit. Claim 3 delete Claim 4 In claim 1 or 2, determining the concentration of the tissue component to be measured according to at least one output light intensity corresponding to the plurality of preset wavelengths comprises: for each preset wavelength among the plurality of preset wavelengths, determining a first output light intensity and a second output light intensity from at least two output light intensities corresponding to the preset wavelength, and determining the concentration of the tissue component to be measured according to the first output light intensity and the second output light intensity corresponding to each preset wavelength; for each preset wavelength among the plurality of preset wavelengths, determining a third output light intensity from at least one output light intensity corresponding to the preset wavelength, and performing differential processing on the third output light intensities corresponding to different preset wavelengths to obtain at least one differential signal, and determining the concentration of the tissue component to be measured according to the at least one differential signal; for each preset wavelength among the plurality of preset wavelengths, determining a fourth output light intensity from at least one output light intensity corresponding to the preset wavelength, and determining the concentration of the tissue component to be measured according to the fourth output light intensity corresponding to each preset wavelength, wherein each A method for measuring tissue components, comprising determining the concentration of the tissue component to be measured according to a first output light intensity and a second output light intensity corresponding to the preset wavelength, by differential processing the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal; and determining the concentration of the tissue component to be measured according to each differential signal corresponding to the preset wavelength. Claim 5 In claim 4, the first output light intensity and the second output light intensity are obtained by collecting at different times by identical or different photosensitive surfaces, the first output light intensity is a systolic light intensity and the second output light intensity is an diastolic light intensity, the photosensitive surfaces include one or more photosensitive surfaces and are intended to output one output light intensity, and the photosensitive surfaces corresponding to the first output light intensity and the second output light intensity are identical or different tissue component measurement methods. Claim 6 In paragraph 4, the first output light intensity corresponding to the preset wavelength is obtained by collecting from a first photosensitive surface comprising one or more photosensitive surfaces corresponding to the preset wavelength, and the second output light intensity corresponding to the preset wavelength is obtained by collecting from a second photosensitive surface comprising one or more photosensitive surfaces corresponding to the preset wavelength, and the average optical path length of the emitted light received at different photosensitive positions of each photosensitive surface among the first photosensitive surfaces belongs to a first average optical path length range, and the first average optical path length range is determined according to a first optical path length average value, which is an average value obtained by calculating the average optical path length of the emitted light received at each photosensitive position of the first photosensitive surface, and the average optical path length of the emitted light received at different photosensitive positions of each photosensitive surface among the second photosensitive surfaces belongs to a second average optical path length range, and the second average optical path length range is each of the A method for measuring tissue components, wherein the second average optical path length is determined by the average value obtained by calculating the average optical path length of the emitted light received at the photosensitive position, the absolute value of the difference between the first average optical path length and the second average optical path length falls within the first optical path length difference range, the fourth output light intensity corresponding to the preset wavelength is obtained by collecting from a photosensitive surface of the same type corresponding to the preset wavelength, and the difference between the average optical path length of the emitted light received at different photosensitive positions of each photosensitive surface among the same types of photosensitive surfaces and the optimal optical path length corresponding to the preset wavelength falls within the second optical path length difference range. Claim 7 In paragraph 2, each of the above photosensitive surfaces includes an annular photosensitive surface or a non-annular photosensitive surface, and the shapes of the different photosensitive surfaces are the same or different, and the same photosensitive surfaces include the annular photosensitive surface or the non-annular photosensitive surface, wherein the same photosensitive surface includes one or more of the photosensitive surfaces, and the same photosensitive surface is for outputting one of the output light intensity, and the same photosensitive surface includes the annular photosensitive surface or the non-annular photosensitive surface, wherein the same photosensitive surface includes one or more of the photosensitive surfaces, and the same photosensitive surface is for outputting one of the output light intensity, and the same photosensitive surface is the annular photosensitive surface, wherein when the same photosensitive surface includes one of the photosensitive surfaces, the same photosensitive surface is an independent annular photosensitive surface; wherein when the same photosensitive surface includes multiple of the photosensitive surfaces, the same photosensitive surface is an annular photosensitive surface formed by a combination of the multiple photosensitive surfaces. A method for measuring tissue components, comprising: a homogeneous photosensitive surface being a non-circular photosensitive surface, wherein when the homogeneous photosensitive surface includes one photosensitive surface, the homogeneous photosensitive surface is an independent non-circular photosensitive surface; and when the homogeneous photosensitive surface includes a plurality of photosensitive surfaces, the homogeneous photosensitive surface is a non-circular photosensitive surface formed by a combination of the plurality of photosensitive surfaces. Claim 8 In paragraph 2, if it is determined that the distance of the homogeneous photosensitive surface from the target area is greater than or equal to a second distance limit, the homogeneous photosensitive surface includes an annular photosensitive surface, a fan-shaped ring photosensitive surface, a fan-shaped photosensitive surface, a circular photosensitive surface, or a square photosensitive surface; if it is determined that the distance of the homogeneous photosensitive surface from the target area is less than or equal to a third distance limit, the shape of the homogeneous photosensitive surface is determined according to the vibration distribution of the injection light, the vibration distribution of the injection light can be decomposed into a vibration distribution along a first direction and a vibration distribution along a second direction, the first direction and the second direction are perpendicular to each other, the ratio of the length of the homogeneous photosensitive surface along the first direction to the length of the homogeneous photosensitive surface along the second direction is determined according to the ratio of the vibration amplitude of the injection light along the first direction to the vibration amplitude of the injection light along the second direction, and the tissue component with the largest vibration amplitude of the injection light along the first direction measurement method. Claim 9 A method for measuring tissue components according to claim 1 or 2, wherein the photosensitive surface is obtained after installing a mask on an initial photosensitive surface, and the shape of the mask is determined according to the shape of the vibration distribution of the emitted light. Claim 10 A method for measuring tissue components according to claim 1 or 2, wherein the intensity distribution of the light spot irradiated by the incident light onto the measurement area is uniform, and the area of ​​the light spot irradiated by the incident light onto the measurement area is greater than or equal to the light spot area limit. Claim 11 A light source module for irradiating a measurement area with incident light of a plurality of preset wavelengths, - each of the incident light is ejected at at least one injection position after passing through the measurement area to form at least one injection light, and the injection position of the incident light includes one -; a collection module comprising M photosensitive surfaces, wherein each of the photosensitive surfaces can collect a light intensity value of the injection light ejected at an injection position within a preset anti-shake range corresponding to the photosensitive surface, and a collection module for obtaining T output light intensities by acquiring a light intensity value corresponding to each of the injection light collected by the M photosensitive surfaces, - each of the output light intensities is obtained by processing the light intensity value of the injection light collected by one or more of the photosensitive surfaces, and 1 ≤ T ≤ M - ; A tissue component measuring device comprising a processing module for determining the concentration of a tissue component to be measured according to at least one output light intensity corresponding to a plurality of preset wavelengths, wherein the ratio of the area of ​​each photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to a ratio limit, said ratio limit is greater than or equal to 0.04 mm, the edge portion represents the perimeter length, and the non-edge portion represents the area, and the ratio in which the average light path length of the emitted light received by the photosensitive surface within the target tissue layer occupies the total light path length is greater than or equal to a ratio limit, or, the total area of ​​the same photosensitive surfaces is determined according to the tissue structure characteristics within the measurement area, said total light path length is the total distance the emitted light is transmitted within the measurement area, said same photosensitive surfaces include at least one photosensitive surface, and said same photosensitive surfaces are for outputting one output light intensity. Claim 12 A measuring component measuring device according to claim 11, further comprising a measuring probe having M photosensitive surfaces and a first sleeve installed therein, wherein a first cross-section representing a cross-section of the first sleeve close to the measuring area extends beyond a target surface of the measuring probe representing a surface close to the measuring area, and a scattering material is installed in at least one of a second cross-section of the first sleeve and an internal area of ​​the first sleeve, wherein the first cross-section and the second cross-section are two cross-sections facing each other, and the internal area includes a part of the internal area or the entire internal area. Claim 13 A measuring component measuring device according to claim 12, further comprising a second sleeve installed outside the target area of ​​the first sleeve, wherein the target area represents a part or the entire area of ​​the first sleeve that extends beyond the target surface of the measuring probe. Claim 14 A tissue component measuring device according to claim 11, wherein a refractive index matching material is filled between the photosensitive surface and the measurement area. Claim 15 A wearable device comprising a tissue component measuring device according to any one of claims 11 to 14, wherein the mass of the wearable device is less than or equal to a mass limit so as to implement that the movement law of the wearable device matches the skin vibration law of the measurement area, and the wearable device causes the movement range of the skin in the measurement area to be less than or equal to a movement range limit. 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