Multi-spectral fusion transcutaneous health index rapid detection device and method

Abstract

The present invention discloses a multi-spectral fusion transcutaneous health index rapid detection device and method, the device includes a mainboard, a light source module and a detector arranged in a housing; the light source module is used to emit monochromatic light under the control of the mainboard, and the monochromatic light irradiates the surface of the detected object after passing through the light output channel; the detector is used to generate a corresponding electrical signal after receiving the monochromatic light refracted and scattered by the detected object, diffused through the light guide channel and adjusted at a specific angle; the mainboard is used to calculate the electrical signal to obtain the calculation result. The present invention can obtain the absorption and fluorescence spectra generated by diffuse reflection of human skin tissue, and perform real-time analysis to obtain multiple health indicators of the human body, including tissue blood oxygen content, heart rate, respiratory rate, bilirubin value, tissue AGEs content, skin cholesterol content, skin water and oil content, etc.

Description

Technical Field

[0001] The present invention relates to the field of detection technology, and in particular to a multi-spectral fusion transcutaneous health index rapid detection device and method. Background Art

[0002] Skin is the largest organ in human tissue, covering the whole body. The surface area of ​​an average adult's skin is 2 square meters. Human skin is a layered structure, divided into three layers, from the outside to the inside, the epidermis, dermis and subcutaneous tissue. The epidermis is the outermost layer of the skin, with a thickness of about 0.037-0.17mm. It can be subdivided into five layers from the outside to the inside, namely the stratum corneum, the clear layer, the granular layer, the spinous layer and the basal layer. The outermost stratum corneum is composed of keratin cells. The deepest basal layer, close to the dermis, is distributed with melanocytes. The dermis is below the epidermis, with a thickness of about 0.6-3mm, and is a semi-solid mixture of collagen fibers, water and matrix. The connective tissue containing nerves and blood vessels is unevenly distributed with absorption components such as hemoglobin, bilirubin, and β-carotene. The subcutaneous tissue is also called the "subcutaneous fat layer". Its thickness varies greatly in different parts of the human body. It is mainly fat, which acts as an insulator and vacuum cleaner. In addition, like the dermis, it is also filled with blood vessels, nerves, and receptors. Moreover, the fat cells it contains are arranged regularly, and can reflect visible light that reaches this layer back to the dermis or epidermis. As the largest organ in the human body, the skin has important physiological functions, such as maintaining the balance between the body and the external environment, reflecting the body's abnormal conditions and lesions, and adjusting the body to adapt to changes in the external environment.

[0003] Human skin is also the main way for light to act on the human body. Visible light or infrared light can enter the human skin tissue to a depth of up to 2-3 cm. During the propagation of light in the skin tissue, photons will undergo varying degrees of absorption, scattering, reflection, refraction, and fluorescence excitation according to the characteristics of different components in the tissue. Therefore, light can be regarded as an information carrier that conveys information about tissue composition and structure. Absorption will cause light to be lost in the tissue. After layers of action, the light that is not absorbed will be transmitted through the tissue boundary and can be collected as detection information. Therefore, the optical detection method of the skin can reflect the detection of various vital health signs and indicators of the human body, which is of great clinical significance.

[0004] For example, the skin is an important site for cholesterol metabolism, and about 11% of the cholesterol in the human body is present in the skin. Skin cholesterol is closely related to cholesterol deposited in the arterial wall. As the degree of arteriosclerosis increases, the cholesterol content in the epidermis also increases. Research results show that skin cholesterol can be used as a new marker for atherosclerosis. High levels of skin cholesterol deposition are an early warning sign of atherosclerosis and can predict the risk of cardiovascular disease.

[0005] In addition, clinical and experimental studies have shown that advanced glycation end products (AGEs) play an important role in the pathophysiology, occurrence and development of diabetic nephropathy, and collagen in the dermis is the main site of AGE accumulation. The accumulation of skin collagen AGEs reflects the accumulation of kidney AGEs. Therefore, by detecting the level of skin AGEs in diabetic patients, it may reflect the early kidney disease of patients to a certain extent.

[0006] In terms of blood oxygen detection, studies have shown that the near-infrared wavelength of 600-900nm is the "spectral window" of human skin tissue. The absorption of light by water and cytochrome is negligible compared to the absorption of hemoglobin, while the concentrations of some other chromophores, such as lipids and melanin, can be considered constant within a certain clinical measurement time. Therefore, it can be considered that there are only two absorbers in human tissue, oxygenated hemoglobin and reduced oxygenated hemoglobin. Moreover, the absorption of light by oxygenated hemoglobin and reduced hemoglobin depends on the wavelength, and they have their own different absorption spectra, so we can determine the absolute or relative content of each component from multiple wavelength absorption spectra, and ultimately achieve non-invasive detection of tissue blood oxygen saturation.

[0007] In the field of neonatology, people have achieved non-invasive detection of transcutaneous bilirubin values ​​through the alternating effects of blue and green light on the skin. Detecting neonatal jaundice is essentially detecting the bilirubin concentration in the newborn. At present, hospitals usually use the bilirubin concentration measured by venous blood test methods or the bilirubin concentration measured by trace blood as the main basis for judgment. Venous blood and trace blood tests are invasive tests. The detection process requires taking heel blood or venous blood from the newborn to obtain serum bilirubin concentration through diazo reagent method, oxidase method and chemical oxidation method. The advantage of this detection method is that it has a high accuracy of about ±5.13μmol / L, but because blood sampling is required, the risk of neonatal infection is increased. Newborns with repeated jaundice symptoms need to repeat blood sampling, which affects the health of newborns. The transcutaneous jaundice detector is a non-invasive test that can quickly detect the bilirubin concentration in the newborn, and plays a significant role in the clinical diagnosis of jaundice.

[0008] In terms of non-invasive blood sugar detection, in 1987, people proposed a method of measuring human blood sugar using near-infrared light, and non-invasive blood sugar measurement methods began to attract the attention of researchers. The principle of this measurement method is as follows: Glucose is the main sugar in the blood, medically known as blood sugar, which contains multiple hydroxyl groups and methyl groups. These hydroxyl groups and methyl groups can produce hydrogen-containing functional groups that absorb near-infrared light under near-infrared light. Near-infrared spectroscopy analysis technology and chemometric methods are used to process these light information, establish a prediction model, and thus calculate blood sugar concentration. This method is expected to be used in wearable devices.

[0009] In addition, in the field of medical beauty, based on the principle of optical detection of the skin, the measurement of skin collagen, moisture, oil, and elasticity can be achieved, and a relatively accurate comprehensive assessment of skin health can be made.

[0010] However, the current methods for detecting human health indicators through the skin have the following problems: First, the existing instrument and equipment design is based on the technical route of traditional optical-mechanical systems, such as cold light sources, lasers, optical fibers, and spectroscopic optical path systems of different specifications. As a result, the equipment is large in size and expensive, and is usually suitable for use in professional places such as hospitals, health examination institutions, and medical beauty institutions, and requires professional operation. The high professionalism of the equipment limits the application of this rapid health detection method in grassroots units such as community hospitals and even ordinary families. Second, due to the special and complex optical properties of the skin, there are multiple effects such as scattering, absorption, and fluorescence after light acts on the skin. Different components of human tissue correspond to different spectral absorption forms and interferences for spectra in different bands, and there is very complex background information. Traditional instruments and equipment using a single spectral analysis method can often only analyze a certain health indicator, and the robustness of the model is poor, which affects the accuracy of the test results. Therefore, based on fusion spectral technology, it is possible to more accurately detect multiple health indicators. Third, thanks to the development of semiconductor materials and microelectronics in recent years, the processing technology and processes of luminescent materials and optical components have made great progress, making it possible to implement traditional optomechanical systems on a smaller scale, providing strong technical support for the sensorization of skin detection devices. However, there are no small-scale skin health detection spectral sensor devices with comprehensive functions and reliable performance. Summary of the invention

[0011] In view of the above technical problems, the present invention provides a multi-spectral fusion transcutaneous health index rapid detection device and method to solve the problems of existing inspection equipment being large in size, expensive, single in detection content and poor in accuracy.

[0012] Other features and advantages of the present disclosure will become apparent from the following detailed description, or may be learned in part by the practice of the present disclosure.

[0013] According to one aspect of the present invention, a multi-spectral fusion transcutaneous health index rapid detection device is disclosed, comprising a main board, a light source module and a detector arranged in a housing, wherein:

[0014] The light source module is used to emit monochromatic light under the control of the mainboard, and the monochromatic light irradiates the surface of the detected object after passing through the light output channel;

[0015] The detector is used to generate a corresponding electrical signal after receiving the monochromatic light refracted and scattered by the detected object, diffused through the light guide channel and adjusted at a specific angle;

[0016] The mainboard is used to calculate the electrical signal to obtain a calculation result.

[0017] Furthermore, the device also includes a light source lens and a detector lens, wherein the detector lens is sleeved in the light source lens, the detector lens and the light source lens form the light output channel, and the detector lens is connected to the light guiding channel.

[0018] Furthermore, a metal cover for achieving light isolation is provided between the light source lens and the detector lens.

[0019] Furthermore, the detector lens is provided with a diffusion film for making the incident direction of the monochromatic light dispersed and uniform, a first aperture for selecting a specific angle for the monochromatic light to pass through, and a second aperture for selecting a specific angle for the monochromatic light to pass through.

[0020] Furthermore, the first aperture is located at an entrance end of the light guiding channel, and the second aperture is located at an exit end of the light guiding channel.

[0021] Furthermore, a linear gradient filter is included, and the linear gradient filter is arranged between the second aperture and the detector, or between the first aperture and the second aperture, and the viewing angle of the linear gradient filter is matched with the exit angle of the second aperture.

[0022] Furthermore, the linear gradient filter includes a plurality of evenly distributed monochromatic wavelength channels for the monochromatic light of different wavelengths to pass through, and the photosensitive array of the detector is arranged corresponding to the monochromatic wavelength channels of the linear gradient filter.

[0023] Furthermore, the light source module includes a plurality of light sources, which include a substrate, a light-emitting chip, and a reflective dam arranged around the edge of the substrate, wherein the light-emitting chips in some of the light sources are surrounded by fluorescent powder, and the light sources are electrically connected to the mainboard so that the plurality of light-emitting chips emit the monochromatic light under the control of the mainboard.

[0024] Furthermore, the mainboard includes an MCU module, a DAC module, a light source driving module, a signal reading module, an ADC module, a temperature measurement module, and an interface module, wherein:

[0025] The MCU module is connected to the DAC module, the ADC module, and the interface module respectively, the DAC module is connected to the light source driving module, the light source driving module is connected to the light source module, the ADC module is connected to the temperature measurement module, the signal reading module is connected to the detector, and the interface module is connected to an external device;

[0026] The MCU module is used to send a trigger signal, which is converted by the DAC module into digital-to-analog signals to drive the light source module to work through the light source driving module, and to calculate the electrical signal read by the signal reading module and the temperature data generated by the temperature measuring module, and output the calculation results to the external device through the interface module.

[0027] According to a second aspect of the present disclosure, a multi-spectral fusion transcutaneous health index rapid detection method is provided, which can be applied to the above-mentioned device, and the method comprises the following steps:

[0028] The detection end of the housing is brought into contact with the surface of the object to be detected;

[0029] The light source module is used to emit monochromatic light through the light output channel to illuminate the surface of the object to be inspected;

[0030] Using a detector to receive the monochromatic light refracted and scattered by the detected object, diffused through a light-guiding channel and adjusted at a specific angle, and generate a corresponding electrical signal;

[0031] The mainboard is used to calculate the electrical signal to obtain a calculation result.

[0032] The technical solution disclosed in this disclosure has the following beneficial effects:

[0033] The device and method include a light source module, a light output channel, a light guide channel, a detector and a main board, which can obtain the absorption, scattering and fluorescence spectra generated by diffuse reflection of human skin tissue, and perform real-time analysis to obtain multiple health indicators of the human body, including tissue blood oxygen content, heart rate, respiratory rate, bilirubin value, tissue AGEs content, skin cholesterol content, etc., skin water and oil content, etc.

[0034] The device is small in size and low in cost, and is suitable for rapid detection of human health indicators in portable instruments and wearable devices. BRIEF DESCRIPTION OF THE DRAWINGS

[0035] Figure 1 This is a schematic diagram of the exploded structure of the detection device in the embodiment of this specification;

[0036] Figure 2 This is a schematic diagram of the structure of the detection device in the embodiment of this specification;

[0037] Figure 3 for Figure 2 AA section view;

[0038] Figure 4 This is a schematic diagram of the structure of a linear gradient filter in an embodiment of this specification;

[0039] Figure 5 This is a corresponding relationship diagram of an exemplary linear gradient filter, a detector photosensitive array, and a spectrum diagram in the embodiments of this specification;

[0040] Figure 6 is a schematic diagram of an exemplary structure of a light source module in an embodiment of this specification;

[0041] Figure 7 is a schematic diagram of an exemplary structure of a light-emitting chip in an embodiment of this specification;

[0042] Figure 8 is a schematic diagram of an exemplary structure of another light-emitting chip in an embodiment of this specification;

[0043] Fig. 9 This is a structural block diagram of the mainboard in the embodiment of this specification;

[0044] Fig.10 Flow chart of the detection method in the embodiments of this specification.

[0045] Reference numerals:

[0046] 1. Shell;

[0047] 2. Mainboard; 201. MCU module; 202. DAC module; 203. Light source driving module; 204. Signal reading module; 205. ADC module; 206. Temperature measurement module; 207. Interface module;

[0048] 3. Light source module; 31. Light emitting source; 310. First light emitting chip; 311. Second light emitting chip; 312. Third light emitting chip; 313. Fourth light emitting chip; 32. Substrate; 33. Reflective dam; 34. Phosphor;

[0049] 4. Detector; 410. Detector photosensitive array;

[0050] 5. Light channel;

[0051] 6. Light guide channel;

[0052] 7. Light source lens;

[0053] 8. Detector lens;

[0054] 9. Metal cover;

[0055] 10. Diffusion membrane;

[0056] 11. First aperture;

[0057] 12. Second aperture;

[0058] 13. Linear gradient filter;

[0059] 14. Connect the bracket;

[0060] 15. Connecting terminals;

[0061] 16. Fix the bracket. DETAILED DESCRIPTION

[0062] The technical solution of the present invention will be described clearly and completely below in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of them. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0063] In the description of the present invention, it should be noted that the terms "center", "upper", "lower", "left", "right", "vertical", "horizontal", "inner", "outer", etc., indicating the orientation or positional relationship, are based on the orientation or positional relationship shown in the drawings, and are only for the convenience of describing the present invention and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore cannot be understood as limiting the present invention. In addition, the terms "first", "second", and "third" are used for descriptive purposes only, and cannot be understood as indicating or implying relative importance.

[0064] In the description of the present invention, it should be noted that, unless otherwise clearly specified and limited, the terms "installed", "connected", and "connected" should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection or an electrical connection; it can be a direct connection, or it can be indirectly connected through an intermediate medium, or it can be the internal communication of two components. For ordinary technicians in this field, the specific meanings of the above terms in the present invention can be understood according to specific circumstances.

[0065] like Figures 1 to 3 As shown, the embodiment of this specification provides a multi-spectral fusion transcutaneous health index rapid detection device, including a main board 2, a light source module 3 and a detector 4 arranged in a housing 1, wherein:

[0066] The light source module 3 is used to emit monochromatic light under the control of the main board 2, and the monochromatic light irradiates the surface of the object to be detected after passing through the light output channel 5;

[0067] The detector 4 is used to generate a corresponding electrical signal after receiving the monochromatic light refracted and scattered by the detected object, diffused and adjusted at a specific angle through the light guide channel 6;

[0068] The main board 2 is used to calculate the electrical signal and obtain the calculation result.

[0069] In one embodiment, the device further includes a light source lens 7 and a detector lens 8 . The detector lens 8 is sleeved in the light source lens 7 . The detector lens 8 and the light source lens 7 form a light output channel 5 . The detector lens 8 is connected to the light guide channel 6 .

[0070] In one embodiment, a metal cover 9 for achieving optical isolation is further provided between the light source lens 7 and the detector lens 8 .

[0071] Among them, exemplary, the shape of the metal cover 9 is consistent with the shape of the outer wall of the detector lens 8, that is, when the detector lens 8 is cylindrical, the metal cover 9 is also cylindrical, and the metal cover 9 wraps the detector lens 8 therein, and in order to save space, the inner wall of the light source lens 7, the metal cover 9 and the outer wall of the detector lens 8 are tightly attached. Exemplarily, the metal cover 9 can also be embedded in the detector lens 8, as long as the metal cover 9 can achieve optical isolation between the light source lens 7 and the detector lens, it is the structural form of the metal cover 9 referred to in the present disclosure.

[0072] In addition, it is worth noting that the light guide channel 6 can be the entire channel from the entrance end of the detector lens 8 to the detector 4, or a certain section of the channel between the entrance end of the detector lens 8 and the detector 4. When the light guide channel 6 is located between the exit end of the detector lens 8 and the detector 4, in order to reduce the volume of the metal cover 9, the detection device can be compact. Figure 1 to Figure 2 As shown, the light source module 3 is arranged between the detector lens 8 and the light guide channel 6, and the light emission direction of the light source module 3 is opposite to the light guide channel 6, so that the emitted light of the light source module 3 does not pollute the light guide channel 6, and the volume of the metal cover 9 is also reduced. At the same time, in this way, the light source module 3 is far away from the main board 2. In actual use, it is necessary to prevent the light source module 3 from loosening and causing the light emission angle to change. Therefore, the present disclosure exemplarily provides a connection method between the light source module 3 and the main board 2, that is, Figure 1 The connecting bracket 14 and the connecting terminal 15 shown can stabilize the connection between the light source module 3 and the mainboard 2 to prevent the light source module 3 from loosening. At the same time, in order to prevent the light guide channel 6 from loosening, a fixing bracket 16 can also be provided to fix the light guide channel 6.

[0073] In one embodiment, the detector lens 8 is provided with a diffusion film 10 that makes the incident direction of the monochromatic light dispersed and uniform, a first aperture 11 for selecting a specific angle of the monochromatic light to pass through, and a second aperture 12 for selecting a specific angle of the monochromatic light to pass through.

[0074] Among them, as a supplement, a lens should be provided at the light incident end of the detector lens 8, and the lens is used to collect monochromatic light and converge the monochromatic light into the detector lens 8. As an example, the diffusion film 10 is specifically a thin film that can scatter light on its surface and spread the light softly and evenly. After the monochromatic light passes through the diffusion film 10, it is selected by the first aperture 11, enters the light guide channel 6 with a certain optical length, and is emitted from the second aperture 12. After this process, it is ensured that the monochromatic light emitted from the second aperture 12 meets the specific incident angle.

[0075] In one embodiment, the first aperture 11 is located at the entrance end of the light guiding channel 6 , and the second aperture 12 is located at the exit end of the light guiding channel 6 .

[0076] That is, the light guiding channel 6 extends from the entrance end of the detector lens 8 to the exit end of the detector lens 8 to reduce the length of the light guiding channel 6 as much as possible, so as to facilitate the selection of monochromatic light of a specific angle. In addition, the optical length of the light guiding channel 6 matches the diameter of the light holes of the first aperture 11 and the second aperture 12. Through this process, it is ensured that the monochromatic light emitted from the second aperture 12 meets the specific incident angle, thereby eliminating the interference of stray light on the detection.

[0077] In one embodiment, a linear gradient filter 13 is also included. The linear gradient filter 13 is arranged between the second aperture 12 and the detector 4, or between the first aperture 11 and the second aperture 12. The viewing angle of the linear gradient filter 13 matches the exit angle of the second aperture 12.

[0078] Among them, the linear gradient filter 13 is used for splitting light, so that the incident light that meets a certain angle and is emitted through the second aperture 12 or the second first aperture 11 is dispersed again into monochromatic light of different wavelengths along the spatial two-dimensional plane direction of the linear gradient filter 13, so as to be detected by the rear-end area array detector. The output signal of the area array detector is finally obtained after the spatial position pixel decoding operation is performed by the mainboard to obtain the required comb spectrum.

[0079] As a supplement, the linear gradient filter 13 includes a plurality of evenly distributed monochromatic wavelength channels for monochromatic lights of different wavelengths to pass through, and the photosensitive array of the detector 4 is arranged corresponding to the monochromatic wavelength channels of the linear gradient filter 13 .

[0080] Among them, exemplary, the linear gradient filter 13 can be a filter made by magnetron sputtering process, with dozens of monochromatic wavelength channels evenly distributed in the wavelength range of 400-1000nm, such as Figure 4The linear gradient filter 13 shown, each rectangular interval corresponds to a specific wavelength of light that can pass through, and has a cutoff depth of more than OD3 for light outside this wavelength. In terms of structure, the filter is accurately aligned with the photosensitive surface of the detector 4. Accordingly, the photosensitive array of the detector 4 is divided into the same number of equally spaced areas, each area corresponding to a specific monochromatic wavelength. In this way, when a beam of complex light passes through the gradient filter, different monochromatic light signals are generated in different pixel areas of the detector 4. The readout circuit of the detector 4 converts the signal value into a digital signal for reading, and then a set of spectrum diagrams can be obtained through the corresponding demodulation algorithm. Specifically, Figure 5 The corresponding relationship diagram of the exemplary linear gradient filter 13, the detector photosensitive array 410, and the spectrum diagram is shown.

[0081] In one embodiment, the light source module 3 includes a plurality of light sources 31, the light sources 31 include a substrate 32, a light-emitting chip, and a reflective dam 33 arranged around the edge of the substrate 32, wherein the light-emitting chips in some of the light sources 31 are surrounded by fluorescent powder 34, and the light sources 31 are electrically connected to the mainboard 2 so that the plurality of light-emitting chips emit monochromatic light under the control of the mainboard 2.

[0082] Among them, exemplary ones are Figures 6 to 8 As shown, the light source 31 may be a UVA ultraviolet light emitting chip based on gallium nitride material, emitting monochromatic light with a half-peak width of no more than 10 nm in the spectral range of 350-395 nm, and exemplarily may adopt a wavelength of 375±5 nm. The number of light emitting chips may be, but is not limited to, four. Figure 7 The first light emitting chip 310 and the second light emitting chip 311 are monochrome light emitting chips, the third light emitting chip 312 and the fourth light emitting chip 313 are monochrome light emitting chips and are surrounded by phosphor 34. Figure 8 As shown, the third light emitting chip 312 and the fourth light emitting chip 313 can emit complex light in the wavelength range of 400-850nm after adding the phosphor 34. The light emitting chip and the phosphor 34 are fixed on the substrate 32 to form an independent light source device, which is connected to the main board 2 by welding, so that the light emitting chip emits monochromatic light under the control of the main board 2.

[0083] The following is a supplement to the working process of the light source module 3 with respect to the above embodiment.

[0084] In a demonstrative detection process, the main board 2 controls the first light-emitting chip 310 and the second light-emitting chip 311, the third light-emitting chip 312 and the fourth light-emitting chip 313 to emit light alternately. First, the first light-emitting chip 310 and the second light-emitting chip 311 are turned on at the same time. At this time, the detector 4 can obtain the fluorescence spectrum of the skin after being excited by high-intensity UVA monochromatic light. It is worth noting that the first light-emitting chip 310 and the second light-emitting chip 311 can also use UVA light-emitting chips with different wavelengths. The main board 2 controls the first light-emitting chip 310 and the second light-emitting chip 311 to turn on at different times, and can respectively obtain the skin fluorescence spectra at different excitation wavelengths, thereby obtaining richer spectral information.

[0085] After the third light-emitting chip 312 and the fourth light-emitting chip 313 are turned on, the detector 4 will obtain the scattering and absorption spectra of the skin to the complex light. Similarly, by mixing different ratios of the phosphor 34 materials, complex light with different spectral ranges and wavelength distributions can be obtained, and the detector 4 will also obtain a richer scattering and absorption spectrum.

[0086] In one embodiment, if Fig. 9 As shown, the main board 2 includes an MCU module 201, a DAC module 202, a light source driving module 203, a signal reading module 204, an ADC module 205, a temperature measurement module 206, and an interface module 207, wherein:

[0087] The MCU module 201 is connected to the DAC module 202, the ADC module 205, and the interface module 207 respectively. The DAC module 202 is connected to the light source driving module 203, the light source driving module 203 is connected to the light source module 3, the ADC module 205 is connected to the temperature measurement module 206, the signal reading module 204 is connected to the detector 4, and the interface module 207 is connected to the external device;

[0088] The MCU module 201 is used to send a trigger signal, which is converted by the DAC module 202 into digital-to-analog signals, to drive the light source module 3 to work through the light source driving module 203, and to calculate the electrical signal read by the signal reading module 204 and the temperature data generated by the temperature measuring module 206, and output the calculation results to the external device through the interface module 207.

[0089] Specifically, the trigger signal sent by the MCU module 201 controls the light source 31 of the light source module 3 to emit light, the detector 4 obtains the fluorescence spectrum data excited after the skin is irradiated with light, the signal reading module 204 sends the fluorescence spectrum data to the MCU module 201, and, when the MCU module 201 sends the trigger signal, it also reads the temperature data detected by the temperature measurement module 206, and then, the MCU module 201 calculates the fluorescence spectrum data and the temperature data respectively. Demonstrably, the calculation process is performed by a firmware program preset in the MCU module 201, and the fluorescence spectrum data and the temperature data can be converted by using a spectrum fusion processing algorithm and a temperature conversion algorithm to obtain the current skin health index data such as tissue blood oxygen content, heart rate, respiratory rate, bilirubin value, tissue AGEs content, skin cholesterol content, skin water and oil content, and body temperature. The health index data is obtained by the fluorescence spectrum data and the temperature data, that is, different health index data are determined by the absorption and fluorescence spectra generated by diffuse reflection of human skin tissue.

[0090] From the above embodiments, it can be seen that the detection device provided by the present invention can obtain the absorption, scattering and fluorescence spectra generated by diffuse reflection of human skin tissue, and perform real-time analysis to obtain multiple health indicators of the human body. It can be compact and low-cost, and is suitable for rapid human health indicator detection in portable instruments and wearable devices.

[0091] Based on the same idea, the exemplary embodiment of the present disclosure also provides a multi-spectral fusion transcutaneous health index rapid detection method, such as Fig.10 As shown, the method includes the following steps S1 to S4:

[0092] Step S1: bringing the detection end of the shell into contact with the surface of the object to be detected.

[0093] Step S2: Using the light source module to emit monochromatic light through the light output channel to illuminate the surface of the object to be detected.

[0094] Step S3: using a detector to receive the monochromatic light refracted and scattered by the detected object, diffused through a light-guiding channel and adjusted at a specific angle, and generating a corresponding electrical signal.

[0095] Step S4: Utilize the mainboard to calculate the electrical signal to obtain a calculation result.

[0096] The above steps S1 to S4 are explained below by way of example, but the present invention is not limited thereto.

[0097] In steps S2 to S4, the original scattering and fluorescence spectra are mainly acquired, preprocessed and fused, and then the characteristic wavelengths of the fused spectrum matrix are extracted and reduced in dimension, and finally a regression model is established to calculate relevant parameters.

[0098] Among them, the acquisition, preprocessing and fusion of the original scattering and fluorescence spectra mainly include: the mainboard controls the lighting of the light-emitting chip, such as the first light-emitting chip 310 and the second light-emitting chip 311 in the above-mentioned device embodiment, to emit ultraviolet monochromatic light to act on human tissue and then excite and produce fluorescence. The fluorescence passes through the array detector and is read out by the readout circuit to obtain a set of mxn matrix signals, where m and n are the number of pixels in the array detector CMOS in the X and Y directions. Since the direction of the linear gradient filter is the X direction, the signal in the Y direction is averaged here to obtain a one-dimensional vector of m elements, which is recorded as vector S1, which is the fluorescence spectrum signal (which contains m elements, and m is the number of pixels in the x direction of the array detector).

[0099] Subsequently, the vector S1 is preprocessed, and the preprocessing exemplarily includes the following steps S201 to S203:

[0100] Step S201: The mainboard reads the spectrum signal value stored in FLSAH and starts the timer.

[0101] Step S202: Perform median filtering with a window of 11 on the data in the spectral signal value to obtain m-10 data processed by precise optical filtering.

[0102] Step S203: Subtract the previous data from the next data to obtain m-11 data, which are arranged in sequence and recorded as vector S1'.

[0103] From the above preprocessing method steps, a preprocessed fluorescence spectrum S1' (including m-11 elements) is obtained.

[0104] Based on the same principle, the MCU module of the mainboard controls the lighting of the light-emitting chip, such as the third light-emitting chip 312 and the fourth light-emitting chip 313 in the above-mentioned device embodiment, to emit complex light to act on human tissue and produce scattering and diffuse reflection. The diffusely reflected light passes through the array detector and is read out by the readout circuit to obtain a set of mxn matrix signals, where m and n are the number of pixels in the array detector CMOS in the X and Y directions. Since the direction of the linear gradient filter is the X direction, the signal in the Y direction is averaged here to obtain a one-dimensional vector of m elements, which is recorded as vector S2, which is the reflected light spectrum signal (which contains m elements, and m is the number of pixels in the x direction of the array detector).

[0105] The reflected light spectrum vector S2 is subjected to the same preprocessing operation to obtain a preprocessed scattered light spectrum S2' (containing m-11 elements).

[0106] Among them, the characteristic wavelength extraction and dimensionality reduction of the fused spectrum matrix mainly include the following:

[0107] For specific health sign parameters, characteristic wavelengths are extracted, that is, the fusion spectrum is reduced in dimension to improve the computational efficiency. The specific method is as follows.

[0108] The experiment prepares samples of physical sign indicators at different concentration levels (specifically obtained from clinical samples, such as infants with different known skin bilirubin content values), and the number of samples is recorded as n. The first step is to collect fused spectral vectors for the n samples. The n fused spectra are arranged to form a matrix S(n,m') with n rows and m' columns. The standard deviation of each column vector of the matrix S is calculated to obtain m' standard deviations δ(1-m'). Here, the threshold β is set, and the standard deviation δ is compared with the threshold β one by one. The column vectors corresponding to δ<β are deleted, and only the column vectors corresponding to δ>β are retained. Finally, m" column vectors are obtained, and the fused spectral matrix S" (n,m") after dimensionality reduction is obtained.

[0109] Among them, the establishment of a regression model to calculate relevant parameters mainly includes:

[0110] The regression model between the fusion spectrum matrix S' and the target detection result (dependent variable) W is established by multivariate linear regression, and the prediction accuracy is verified by calculating the correlation coefficient and the sum of square errors between the predicted result and the true value. Taking skin bilirubin as an example, W is a column vector with n rows and 1 column, and each element corresponds to a different skin bilirubin value.

[0111] Multiple Linear Regression Model:

[0112] W=SK+E

[0113] Where W is the dependent variable matrix, S is the independent variable matrix, K is the coefficient matrix, and E is the error matrix

[0114] When W and S are known, K and E are obtained through the following matrix operation, thereby obtaining the bilirubin prediction model.

[0115] K=(S'S) -1 S'W

[0116] E=W-SK

[0117] Where S' is the transposed matrix of S, (S'S) -1 represents the inverse matrix of S'S.

[0118] The specific details of the above method have been described in detail in the implementation method of the device part. The undisclosed details can be found in the implementation method of the device part, so they will not be repeated here.

[0119] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit them; although the present invention is described in detail with reference to the above embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the above embodiments, or replace some or all of the technical features therein by equivalents; and these modifications or replacements do not make the essence of the corresponding technical solutions deviate from the scope of the technical solutions of the embodiments of the present invention. In addition, those skilled in the art can understand that although some embodiments described herein include certain features included in other embodiments instead of other features, the combination of features of different embodiments means that they are within the scope of the present invention and form different embodiments. For example, in the above claims, any one of the embodiments claimed for protection can be used in any combination. The information disclosed in this background technology section is only intended to deepen the understanding of the overall background technology of the present invention, and should not be regarded as admitting or suggesting in any form that the information constitutes prior art known to those skilled in the art.

Claims

1. A multi-spectral fusion transcutaneous health index rapid detection device, characterized in that: It includes a mainboard, a light source module and a detector arranged in a housing, wherein: The light source module is used to emit monochromatic light under the control of the mainboard, and the monochromatic light irradiates the surface of the detected object after passing through the light output channel; The detector is used to generate a corresponding electrical signal after receiving the monochromatic light refracted and scattered by the detected object, diffused through the light guide channel and adjusted at a specific angle; The mainboard is used to calculate the electrical signal to obtain a calculation result; And, the light source module includes a light emitting light source, the light emitting light source is electrically connected to the mainboard, the light emitting light source includes a substrate, a light emitting chip, and a reflective dam arranged around the edge of the substrate, the light emitting light source is specifically a first light emitting chip, a second light emitting chip, a third light emitting chip and a fourth light emitting chip, wherein the third light emitting chip and the fourth light emitting chip are surrounded by phosphors, the first light emitting chip and the second light emitting chip emit the monochromatic light under the control of the mainboard, the third light emitting chip and the fourth light emitting chip emit polychromatic light, and the mainboard controls the first light emitting chip and the second light emitting chip, the third light emitting chip and the fourth light emitting chip to emit light alternately; The device also includes a light source lens and a detector lens, wherein the detector lens is sleeved in the light source lens, the detector lens and the light source lens form the light output channel, the detector lens is connected to the light guide channel, a metal cover for achieving light isolation is also arranged between the light source lens and the detector lens, and the detector lens is sequentially provided with a diffusion film for making the incident direction of the monochromatic light dispersed and uniform, a first aperture for selecting a specific angle for the monochromatic light to pass through, and a second aperture for selecting a specific angle for the monochromatic light to pass through.

2. The multi-spectral fusion transcutaneous health index rapid detection device according to claim 1 is characterized in that: The first aperture is located at the entrance end of the light guiding channel, and the second aperture is located at the exit end of the light guiding channel.

3. The multi-spectral fusion transcutaneous health index rapid detection device according to claim 1 is characterized in that: It also includes a linear gradient filter, which is arranged between the second aperture and the detector, or between the first aperture and the second aperture, and the viewing angle of the linear gradient filter matches the exit angle of the second aperture.

4. The multi-spectral fusion transcutaneous health index rapid detection device according to claim 3 is characterized in that: The linear gradient filter comprises a plurality of evenly distributed monochromatic wavelength channels for the monochromatic light of different wavelengths to pass through, and the photosensitive array of the detector is arranged corresponding to the monochromatic wavelength channels of the linear gradient filter.

5. The multi-spectral fusion transcutaneous health index rapid detection device according to claim 1 is characterized in that: The main board includes an MCU module, a DAC module, a light source driving module, a signal reading module, an ADC module, a temperature measurement module, and an interface module, wherein: The MCU module is connected to the DAC module, the ADC module, and the interface module respectively, the DAC module is connected to the light source driving module, the light source driving module is connected to the light source module, the ADC module is connected to the temperature measurement module, the signal reading module is connected to the detector, and the interface module is connected to an external device; The MCU module is used to send a trigger signal, which is converted by the DAC module into digital-to-analog signals to drive the light source module to work through the light source driving module, and to calculate the electrical signal read by the signal reading module and the temperature data generated by the temperature measuring module, and output the calculation results to the external device through the interface module.

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