CN114305336A

CN114305336A - Multi-spectral fusion percutaneous health index rapid detection device and method

Info

Publication number: CN114305336A
Application number: CN202111630258.6A
Authority: CN
Inventors: 付庆波; 刘鑫
Original assignee: Atombit Technology Co ltd
Current assignee: He Xian
Priority date: 2021-12-28
Filing date: 2021-12-28
Publication date: 2022-04-12

Abstract

The invention discloses a device and a method for quickly detecting a multispectral fusion percutaneous health index, wherein the device comprises a main board, a light source module and a detector which are arranged in a shell; the light source module is used for emitting monochromatic light under the control of the main board, and the monochromatic light irradiates the surface of the detected object after passing through the light emitting channel; the detector is used for receiving monochromatic light which is refracted and scattered by the detected object, diffused by the light guide channel and adjusted by a specific angle, and then generating a corresponding electric signal; and the mainboard is used for calculating the electric signals to obtain a calculation result. The invention can obtain absorption and fluorescence spectra generated by diffuse reflection of human skin tissues, and carry out real-time analysis to obtain a plurality of human health indexes, including tissue blood oxygen content, heart rate, respiratory rate, bilirubin value, tissue AGEs content, skin cholesterol content, skin moisture oil content and the like.

Description

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

Technical Field

The invention relates to the technical field of detection, in particular to a device and a method for quickly detecting a multispectral fusion percutaneous health index.

Background

The skin is the largest organ in human tissue, covers the whole body, and the surface area of the skin of a common adult is 2 square meters. The human skin is a layered structure, which is divided into 3 layers, namely, the epidermis, the dermis and the subcutaneous tissue from outside to inside. The epidermis is the outermost layer of the skin, has a thickness of about 0.037-0.17mm, and can be subdivided into five layers from outside to inside, namely a cuticle layer, a stratum lucidum layer, a granule layer, a spinous layer and a basal layer in sequence. The outermost stratum corneum is built up by keratin cells. The deepest basal layer, which is next to the dermis, has melanocytes distributed. The dermis, which is below the epidermis and approximately 0.6-3mm thick, is a semi-solid mixture of collagen fibers, water and matrix. Connective tissue including nerves and blood vessels, and absorbing components such as hemoglobin, bilirubin, beta-carotene, etc. are unevenly distributed. The subcutaneous tissue, also known as the "subcutaneous fat layer," has a large difference in thickness at different parts of the body, mainly fat, and functions as an insulator and a vacuum cleaner. In addition, blood vessels, nerves, receptors, and the like are distributed inside the dermis. And the fat cells are regularly arranged, and can reflect the visible light reaching the layer back to the dermis or epidermis layer. The skin, the largest organ of human tissue, is responsible for important physiological functions. For example, the balance between the inside of the body and the external environment is maintained, the abnormal condition and pathological changes of the body are reflected, and the body is adjusted to adapt to the change of the external environment.

Human skin is also the main route of light to the human body. Visible light or infrared light can enter human skin tissue to a depth of up to 2-3 cm. In the process of light propagation in skin tissue, photons can have different degrees of absorption, scattering, reflection, refraction, fluorescence excitation and the like according to the characteristics of different components in the tissue, so that the light can be regarded as an information carrier for conveying information of the tissue components and the structure. Absorption causes light to be lost in the tissue, and eventually, the light that is not absorbed through layer-by-layer interaction is 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 sign indexes of a human body, and has important significance in clinic.

For example, the skin is an important site of cholesterol metabolism, and about 11% of cholesterol is present in the skin of the human body. Skin cholesterol is closely related to the cholesterol deposited in the arterial wall, and as the degree of arteriosclerosis increases, the cholesterol level in the epidermal layer also increases. Research results show that the skin cholesterol can be used as a novel marker of atherosclerosis, high-level skin cholesterol deposition is an early warning signal of atherosclerosis, and risk prediction of cardiovascular diseases can be realized;

in addition, clinical and experimental studies show that advanced glycation end products (AGEs) play an important role in pathophysiology, occurrence and development of diabetic nephropathy, collagen in the dermis of the skin is the main gathering place of the AGEs, and the accumulation of the collagen AGEs in the skin reflects the accumulation of the AGEs in the kidney. Therefore, the detection of skin AGEs levels in diabetic patients may reflect, at some level, the condition of early renal lesions in patients.

In the aspect of blood oxygen detection, research shows that the wavelength of near infrared 600-900 nm is in a spectrum window of human skin tissues. Water and cytochromes absorb light negligibly compared to hemoglobin, while other chromophores, such as lipids and melanin, whose concentration can be considered constant over a certain clinical measurement time. Therefore, it is considered that only two absorbers of oxyhemoglobin and reduced oxyhemoglobin exist in human tissue. And the absorption of light by oxyhemoglobin and reduced hemoglobin depends on wavelength, and the oxyhemoglobin and the reduced hemoglobin have different absorption lines, so that the absolute content or the relative content of each component can be determined from a plurality of wavelength absorption spectrums, and finally, the noninvasive detection of the blood oxygen saturation of the tissues can be realized.

In the field of newborn pediatrics, people realize noninvasive detection of the percutaneous bilirubin value through the alternate action of blue-green light on the skin. The essence of detecting neonatal jaundice is to detect bilirubin levels in the neonate. At present, the bilirubin concentration measured by a venous blood test method or the bilirubin concentration measured by trace blood is generally used as a main judgment basis in hospitals. Venous blood and trace blood tests belong to invasive tests. The method has the advantages that the accuracy is high and is about +/-5.13 mu mol/L, but because blood needs to be collected, the risk of infection of the newborn is increased, the blood needs to be repeatedly collected for the newborn with repeated jaundice symptoms, and the health of the newborn is influenced. The percutaneous jaundice detector belongs to noninvasive detection, can quickly detect bilirubin concentration in a newborn infant, and plays an important role in clinical jaundice diagnosis.

In the aspect of noninvasive blood glucose detection, a method for measuring blood glucose of a human body by adopting near infrared light is proposed in 1987, and a noninvasive blood glucose measurement method is concerned by researchers. The principle of the measurement method is as follows: glucose is the main sugar in blood, is medically called blood sugar, and comprises a plurality of hydroxyl groups and methyl groups, the hydroxyl groups and the methyl groups can generate hydrogen-containing functional groups for absorbing near infrared light under the near infrared light, and the light information is processed by using a near infrared spectrum analysis technology and a chemometric method to establish a prediction model so as to calculate the blood sugar concentration. This method is promising for application in wearable devices.

In addition, in the field of medical science and beauty, based on the optical detection principle of skin, the measurement of collagen, water, oil and elasticity of the skin is realized, so that the comprehensive evaluation of the health degree of the skin can be relatively accurately carried out, and the like.

However, the current method for detecting the human health index through the skin has the following problems: first, the existing instrument and device design implements a technical route based on a conventional optical-mechanical system, such as cold light sources, lasers, optical fibers, and light splitting optical path systems of different specifications. The equipment is large in size and high in price, is usually suitable for being used in professional places such as hospitals, health examination institutions and medical and American institutions, and needs to be operated by professional personnel. The device has strong specialty, and the application of the rapid health detection method in the basal layer units such as community hospitals and the like and even common families is limited. Secondly, due to the particularly complex optical properties of the skin, there are various effects of scattering, absorption, fluorescence, etc. after the light acts on the skin. Different components of human tissues correspond to different spectral absorption forms and interferences on spectra of different wave bands, and very complex background information exists. The traditional instrument and equipment adopting the single spectrum analysis method can only analyze one health index, and the robustness of the model is poor, so that the accuracy of the detection result is influenced. Therefore, the detection of multiple health indexes can be realized more accurately based on the fusion spectrum technology. Thirdly, thanks to the development of semiconductor materials and microelectronics in recent years, the processing techniques and processes of luminescent materials and optical components have been greatly developed, so that the conventional optical-mechanical system can be realized in a smaller scale, and powerful technical support is provided for the sensification of the skin detection device. However, a small skin health detection spectrum sensor device with complete functions and reliable performance is not seen at present.

Disclosure of Invention

In view of the technical problems, the invention provides a device and a method for rapidly detecting a multispectral fusion percutaneous health index, which solve the problems of large volume, high price, single detection content and poor precision of the existing detection equipment.

Additional features and advantages of the disclosure will be set forth in the detailed description which follows, or in part will be obvious from the description, or may be learned by practice of the disclosure.

According to one aspect of the invention, a multispectral fusion percutaneous health indicator rapid detection device is disclosed, which comprises a main board, a light source module and a detector which are arranged in a shell, wherein,

the light source module is used for emitting monochromatic light under the control of the mainboard, and the monochromatic light irradiates the surface of the detected object after passing through the light emitting channel;

the detector is used for receiving the monochromatic light which is refracted and scattered by the detected object, diffused by the light guide channel and adjusted by a specific angle, and then generating a corresponding electric signal;

the mainboard is used for calculating the electric signal to obtain a calculation result.

Further, the device still includes light source camera lens and detector camera lens, the detector camera lens cover is located in the light source camera lens, the detector camera lens with enclose between the light source camera lens and constitute the light-emitting channel, the detector camera lens is connected the leaded light passageway.

Further, a metal cover used for achieving optical isolation is further arranged between the light source lens and the detector lens.

Furthermore, a diffusion film for enabling the incidence direction of the monochromatic light to become dispersed and uniform, a first diaphragm for selecting the specific angle of the monochromatic light to pass through and a second diaphragm for selecting the specific angle of the monochromatic light to pass through are sequentially arranged in the detector lens.

Further, the first diaphragm is located at an inlet end of the light guide channel, and the second diaphragm is located at an outlet end of the light guide channel.

Furthermore, the optical fiber laser device further comprises a linear gradient filter, wherein the linear gradient filter is arranged between the second diaphragm and the detector or between the first diaphragm and the second diaphragm, and the visual angle field of the linear gradient filter is matched with the emergence angle of the second diaphragm.

Furthermore, the linear gradient filter comprises a plurality of monochromatic wavelength channels which are uniformly distributed and are used for allowing the monochromatic light with 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.

Furthermore, the light source module comprises a plurality of light-emitting light sources, each light-emitting light source comprises a substrate, light-emitting chips and a light-reflecting dam surrounding the edge of the substrate, wherein fluorescent powder is filled around the light-emitting chips in part of the light-emitting light sources, and the light-emitting light sources are electrically connected with the main board, so that the plurality of light-emitting chips emit the monochromatic light under the control of the main board.

Further, the mainboard includes MCU module, DAC module, light source drive module, signal reading module, ADC module, temperature measurement module, interface module, wherein:

the MCU module is respectively connected with the DAC module, the ADC module and the interface module, the DAC module is connected with the light source driving module, the light source driving module is connected with the light source module, the ADC module is connected with the temperature measuring module, the signal reading module is connected with the detector, and the interface module is connected with external equipment;

the MCU module is used for sending a trigger signal, performing digital-to-analog conversion on the trigger signal through the DAC module, driving the light source module to work through the light source driving module, calculating the electric signal read by the signal reading module, calculating temperature data generated by the temperature measuring module, and outputting a calculation result to the external equipment through the interface module.

According to a second aspect of the present disclosure, there is provided a method for rapidly detecting a multispectral fusion percutaneous health indicator, which can be applied to the above device, the method including the following steps:

contacting the detection end of the shell with the surface of the detected object;

emitting monochromatic light by using a light source module, and irradiating the surface of the detected object after the monochromatic light passes through a light outlet channel;

the monochromatic light which is refracted and scattered by the detected object and is diffused through a light guide channel and adjusted by a specific angle is received by a detector to generate a corresponding electric signal;

and calculating the electric signal by using the mainboard to obtain a calculation result.

The technical scheme of the disclosure has the following beneficial effects:

the device and the method comprise a light source module, a light outlet channel, a light guide channel, a detector and a mainboard, and can acquire absorption, scattering and fluorescence spectra generated by diffuse reflection of human skin tissues, and perform real-time analysis to obtain a plurality of human health indexes including tissue blood oxygen content, heart rate, respiration rate, bilirubin value, tissue AGEs content, skin cholesterol content and the like, skin moisture oil content and the like.

The device has small volume and low cost, and is suitable for rapid human health index detection applied to portable instruments and wearable equipment.

Drawings

FIG. 1 is an exploded view of a detecting device in an embodiment of the present disclosure;

FIG. 2 is a schematic structural diagram of a detection device in an embodiment of the present disclosure;

FIG. 3 is a sectional view taken along line A-A of FIG. 2;

FIG. 4 is a schematic structural diagram of a linear graded filter in an embodiment of the present disclosure;

FIG. 5 is a diagram illustrating exemplary correspondence between a linear graded filter, a detector photosensitive array, and a spectrogram in an embodiment of the present disclosure;

fig. 6 is an exemplary structural diagram of a light source module in an embodiment of the present disclosure;

fig. 7 is a schematic view of an exemplary structure of a light emitting chip in an embodiment of the present specification;

fig. 8 is a schematic view of an exemplary structure of another light emitting chip in the embodiments of the present specification;

fig. 9 is a block diagram of a structure of a motherboard in an embodiment of the present specification;

fig. 10 is a flowchart of a detection method in an embodiment of the present disclosure.

Reference numerals:

1. a housing;

2. a main board; 201. an MCU module; 202. a DAC module; 203. a light source driving module; 204. a signal reading module; 205. an ADC module; 206. a temperature measuring module; 207. an interface module;

3. a light source module; 31. a light emitting source; 310. a first light emitting chip; 311. a second light emitting chip; 312. a third light emitting chip; 313. a fourth light emitting chip; 32. a substrate; 33. a light reflecting dam; 34. fluorescent powder;

4. a detector; 410. a detector photosensitive array;

5. a light exit channel;

6. a light guide channel;

7. a light source lens;

8. a detector lens;

9. a metal cover;

10. a diffusion membrane;

11. a first diaphragm;

12. a second diaphragm;

13. a linear graded filter;

14. connecting a bracket;

15. a connection terminal;

16. and fixing the bracket.

Detailed Description

The technical solutions of the present invention will be described clearly and completely with reference to the accompanying drawings, and it should be understood that the described embodiments are some, but not all embodiments of the present invention. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.

In the description of the present invention, it should be noted that the terms "center", "upper", "lower", "left", "right", "vertical", "horizontal", "inner", "outer", and the like indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings, and are only for convenience of description and simplicity of description, but do not indicate or imply that the device or element being referred to must have a specific orientation, be constructed and operated in a specific orientation, and thus, should not be construed as limiting the present invention. Furthermore, the terms "first," "second," and "third" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance.

In the description of the present invention, it should be noted that, unless otherwise explicitly specified or limited, the terms "mounted," "connected," and "connected" are to be construed broadly, e.g., as meaning either a fixed connection, a removable connection, or an integral connection; can be mechanically or electrically connected; they may be connected directly or indirectly through intervening media, or they may be interconnected between two elements. The specific meanings of the above terms in the present invention can be understood in specific cases to those skilled in the art.

As shown in fig. 1 to 3, an embodiment of the present disclosure provides a device for rapidly detecting a multispectral fusion transcutaneous health indicator, including a main board 2, a light source module 3 and a detector 4 disposed in a housing 1, wherein,

the light source module 3 is used for emitting monochromatic light under the control of the mainboard 2, and the monochromatic light irradiates the surface of the detected object after passing through the light emitting channel 5;

the detector 4 is used for receiving monochromatic light which is refracted and scattered by the detected object, diffused by the light guide channel 6 and adjusted by a specific angle, and then generating a corresponding electric signal;

and the mainboard 2 is used for calculating the electric signals to obtain a calculation result.

In an 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, a light exit channel 5 is formed between the detector lens 8 and the light source lens 7, and the detector lens 8 is communicated with the light guide channel 6.

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

In an exemplary embodiment, the shape of the metal cover 9 is identical to the outer wall shape of the detector lens 8, that is, when the detector lens 8 is cylindrical, the metal cover 9 is also cylindrical, the metal cover 9 encloses the detector lens 8, 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 closely attached. Exemplarily, a metal cover 9 may be embedded in the detector lens 8, and the metal cover 9 may be a structural form of the metal cover 9 referred to in the present disclosure as long as the metal cover 9 can realize optical isolation between the light source lens 7 and the detector lens.

In addition, it should be noted that the light guide channel 6 may be a whole channel from the entrance end of the detector lens 8 to the detector 4, or a certain channel from the entrance end of the detector lens 8 to the detector 4, when the light guide channel 6 is located between the exit end of the detector lens 8 and the detector 4, because the volume of the metal cover 9 is reduced, the detection device has a small volume, as shown in fig. 1 to 2, the light source module 3 is disposed between the detector lens 8 and the light guide channel 6, and the light exit direction of the light source module 3 faces away from the light guide channel 6, so that the light emitted from the light source module 3 does not pollute the light guide channel 6, and the volume of the metal cover 9 is also reduced, meanwhile, the light source module 3 is far away from the motherboard 2, which needs to prevent the light source module 3 from loosening to cause the problem of light exit angle change in practical use, therefore, the present disclosure exemplarily provides a connection manner of the light source module 3 and the main board 2, that is, the connection bracket 14 and the connection terminal 15 shown in fig. 1, which can stabilize the connection of the light source module 3 and the main board 2, and prevent the light source module 3 from loosening, and at the same time, in order to prevent the light guide channel 6 from loosening, a fixing bracket 16 for fixing the light guide channel 6 may be further provided.

In one embodiment, a diffusion film 10 for making the incident direction of the monochromatic light become dispersed and uniform, a first diaphragm 11 for selecting a specific angle of the monochromatic light to pass through, and a second diaphragm 12 for selecting a specific angle of the monochromatic light to pass through are sequentially disposed in the detector lens 8.

Wherein, as supplementary, the light incident end of detector camera lens 8 should be provided with a lens, lens are used for collecting monochromatic light, in monochromatic light assembles detector camera lens 8, as the exemplarily, diffusion barrier 10 specifically is for can making light can take place the scattering on its surface, the film that soft even scattering of light comes out, monochromatic light passes through diffusion barrier 10 back, select through first diaphragm 11, enter into the light guide channel 6 that has certain optical length, from the emergence in second diaphragm 12, through this process, in order to guarantee that the monochromatic light from the emergence of second diaphragm 12 satisfies specific incident angle.

In one embodiment, a first diaphragm 11 is located at the entrance end of the light-conducting channel 6 and a second diaphragm 12 is located at the exit end of the light-conducting channel 6.

That is, the light guide 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 guide channel 6 as much as possible, which facilitates selection of monochromatic light at a specific angle, and as a supplement, the optical length of the light guide channel 6 matches with the diameters of the light through holes of the first diaphragm 11 and the second diaphragm 12, through this process, to ensure that the monochromatic light emitted from the second diaphragm 12 satisfies a specific incident angle, thereby eliminating the interference of stray light on detection.

In an embodiment, a linear gradient filter 13 is further included, the linear gradient filter 13 is disposed between the second diaphragm 12 and the detector 4, or between the first diaphragm 11 and the second diaphragm 12, and a viewing field of the linear gradient filter 13 matches with an emergence angle of the second diaphragm 12.

The linear gradient filter 13 is configured to split light, so that incident light that is emitted from the second diaphragm 12 or the second first diaphragm 11 and satisfies a certain angle is re-dispersed into monochromatic light with different wavelengths along the spatial two-dimensional plane direction of the linear gradient filter 13, so as to be detected by the area array detector at the rear end, and an output signal of the area array detector is subjected to spatial position pixel decoding operation by the main board to finally obtain a required comb spectrum.

In addition, the linear graded filter 13 includes a plurality of monochromatic wavelength channels uniformly distributed for monochromatic light with different wavelengths to pass through, and the photosensitive array of the detector 4 is arranged corresponding to the monochromatic wavelength channels of the linear graded filter 13.

In an exemplary embodiment, the linear graded filter 13 may be made by a magnetron sputtering process, and several tens of filters with monochromatic wavelength channels are uniformly distributed in a wavelength range of 400-1000nm, such as the linear graded filter 13 shown in fig. 4, where the interval of each rectangle corresponds to light with a specific wavelength and the light other than the wavelength has a cut-off depth of more than OD3, structurally, the filter is accurately aligned with the photosensitive surface of the detector 4, and correspondingly, the photosensitive array of the detector 4 is divided into equal-interval regions with the same number, and each region corresponds to a specific monochromatic wavelength, so that after a beam of polychromatic light passes through the graded filter, different monochromatic light signals are correspondingly generated in different pixel regions of the detector 4. The detector 4 reading circuit converts the signal value into a digital signal for reading, and then a corresponding demodulation algorithm can be used to obtain a set of spectrograms, specifically, the corresponding relationship graph of the exemplary linear gradient filter 13, the detector photosensitive array 410 and the spectrograms shown in fig. 5.

In an embodiment, the light source module 3 includes a plurality of light emitting sources 31, each of the light emitting sources 31 includes a substrate 32, light emitting chips, and a light reflecting dam 33 surrounding an edge of the substrate 32, wherein the periphery of the light emitting chips in the light emitting sources 31 is filled with fluorescent powder 34, and the light emitting sources 31 are electrically connected to the motherboard 2, so that the plurality of light emitting chips emit monochromatic light under the control of the motherboard 2.

In fig. 6 to 8, the light source 31 may be a UVA ultraviolet light emitting chip based on a gallium nitride material, and emits monochromatic light with a half-peak width not greater than 10nm in a spectrum range of 350-395nm, and may exemplarily adopt wavelengths of 375 ± 5nm, the number of the light emitting chips may be, but is not limited to, four, in fig. 7, the first light emitting chip 310 and the second light emitting chip 311 are monochromatic light emitting chips, the third light emitting chip 312 and the fourth light emitting chip 313 are monochromatic light emitting chips, and the periphery thereof is filled with the phosphor powder 34, as shown in fig. 8, the third light emitting chip 312 and the fourth light emitting chip 313 added with the phosphor powder 34 may emit polychromatic light in a wavelength range of 400-850 nm. The light emitting chip and the phosphor powder 34 are fixed on the substrate 32 to form an independent light source device, and the light source device is connected with the motherboard 2 in a welding manner, so that the light emitting chip emits monochromatic light under the control of the motherboard 2.

Hereinafter, the working flow of the light source module 3 is supplemented to the above embodiment.

In an exemplary detection process, the main board 2 controls the first light emitting chip 310 and the second light emitting chip 311, and the third light emitting chip 312 and the fourth light emitting chip 313 to alternately emit light, first, the first light emitting chip 310 and the second light emitting chip 311 are simultaneously turned on, at this time, the detector 4 can obtain a fluorescence spectrum excited after the skin is irradiated by high-intensity UVA monochromatic light, and it is noted that the first light emitting chip 310 and the second light emitting chip 311 can also adopt UVA light emitting chips with different wavelengths, and the main board 2 controls the first light emitting chip 310 and the second light emitting chip 311 to be turned on at different times, and can respectively obtain a skin fluorescence spectrum under different excitation wavelengths, thereby obtaining richer spectrum information.

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 spectrum of the skin to the polychromatic light. Similarly, by blending different phosphor 34 material ratios, polychromatic light with different spectral ranges and wavelength distributions can be obtained, and the detector 4 will also obtain richer scattering and absorption spectra.

In an embodiment, as shown in fig. 9, 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 thermometry module 206, and an interface module 207, where:

the MCU module 201 is respectively connected with the DAC module 202, the ADC module 205 and the interface module 207, the DAC module 202 is connected with the light source driving module 203, the light source driving module 203 is connected with the light source module 3, the ADC module 205 is connected with the temperature measuring module 206, the signal reading module 204 is connected with the detector 4, and the interface module 207 is connected with external equipment;

the MCU module 201 is configured to send a trigger signal, perform digital-to-analog conversion on the trigger signal through the DAC module 202, drive the light source module 3 to operate through the light source driving module 203, calculate the electrical signal read by the signal reading module 204, calculate the temperature data generated by the temperature measuring module 206, and output the calculation result to an external device through the interface module 207.

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 fluorescence spectrum data excited after irradiation of skin light, the signal reading module 204 sends the fluorescence spectrum data to the MCU module 201, and the MCU module 201 sends the trigger signal and also reads temperature data detected by the temperature measuring module 206, and then the MCU module 201 calculates the fluorescence spectrum data and the temperature data, illustratively, the calculation process is performed by a firmware program preset in the MCU module 201, and data conversion can be performed on the fluorescence spectrum data and the temperature data by using, for example, a spectrum fusion processing algorithm and a temperature conversion algorithm, so as to obtain current skin health index data, such as tissue blood oxygen content, heart rate, respiration rate, bilirubin value, tissue AGEs content, skin cholesterol content, and skin moisture oil content, The body temperature, the health index data are obtained from fluorescence spectrum data and temperature data, namely different health index data are determined by absorption and fluorescence spectrum generated by diffuse reflection of human skin tissue.

According to the embodiment, the detection device provided by the disclosure can acquire absorption, scattering and fluorescence spectra generated by diffuse reflection of human skin tissues, and performs real-time analysis to obtain a plurality of human health indexes, so that the detection device has the advantages of small size and low cost, and is suitable for rapid human health index detection in portable instruments and wearable equipment.

Based on the same idea, an exemplary embodiment of the present disclosure further provides a method for rapidly detecting a multispectral fusion transcutaneous health indicator, as shown in fig. 10, where the method includes the following steps S1 to S4:

and step S1, contacting the detection end of the shell with the surface of the detected object.

And step S2, emitting monochromatic light by the light source module to irradiate the surface of the detected object after passing through the light outlet channel.

And step S3, receiving the monochromatic light refracted and scattered by the detected object and diffused by the light guide channel and adjusted by a specific angle by using a detector to generate a corresponding electric signal.

And step S4, calculating the electric signal by using the main board to obtain a calculation result.

The following exemplarily explains the above steps S1 to S4, but the present invention is not limited thereto.

In steps S2-S4, the original scattering and fluorescence spectra are mainly acquired, preprocessed and fused, then the characteristic wavelength of the fused spectrum matrix is extracted and dimension is reduced, and finally a regression model is established for relevant parameter calculation.

The acquisition, pretreatment and fusion of the original scattering and fluorescence spectrum mainly comprise the following steps: the mainboard controls and lights up the light emitting chips, such as the first light emitting chip 310 and the second light emitting chip 311 in the above device embodiments, and the ultraviolet monochromatic light is emitted to act on the human tissue and then is excited to generate fluorescence. The fluorescence is read out by a reading circuit after passing through the array detector, so that a group of mxn matrix signals is obtained, wherein m and n are the number of pixels of 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 to obtain a one-dimensional vector of m elements, which is denoted as vector S1, i.e. the fluorescence spectrum signal (which includes m elements, where m is the number of pixels in the X direction of the array detector).

Subsequently, preprocessing is performed on the vector S1, which illustratively includes the following steps S201 to S203:

step S201: the main board reads the spectrum signal value stored in the FLSAH, and starts a timer.

Step S202: and (4) carrying out median filtering with a window of 11 on the data in the spectrum signal value to obtain m-10 data subjected to fine filtering processing.

Step S203: the next data is subtracted from the previous data to yield m-11 data, which are arranged in sequence and designated as vector S1'.

From the above-described pretreatment method step, a pretreated fluorescence spectrum S1' (containing m-11 elements) was obtained.

Based on the same principle, the MCU module of the motherboard controls the lighting of the light emitting chips, such as the third light emitting chip 312 and the fourth light emitting chip 313 in the above embodiments of the devices, to emit polychromatic light to act on human tissues, thereby generating scattering and diffuse reflection. The diffuse reflection light passes through the array detector and is read out by a reading circuit, so that a group of mxn matrix signals is obtained, wherein m and n are the number of pixels of the array detector CMOS in the X direction and the Y direction. Since the direction of the linear gradient filter is the X direction, the signal in the Y direction is averaged to obtain a one-dimensional vector of m elements, which is denoted as vector S2, i.e. the reflected light spectrum signal (which includes m elements, where m is the number of pixels in the X direction of the array detector).

The same principle preprocessing operation is performed on the reflected light spectrum vector S2 to obtain a preprocessed scattered light spectrum S2' (containing m-11 elements).

The method mainly comprises the following steps of extracting characteristic wavelengths of the fusion spectrum matrix and reducing dimensions:

and (3) extracting characteristic wavelengths aiming at specific health sign parameters, namely reducing the dimension of the fusion spectrum to achieve the purpose of improving the operation efficiency. The specific method is as follows.

The experiment prepares sign index samples of different concentration levels, (obtained specifically from clinical samples such as infants with known values of different skin bilirubin content), and the number of samples is recorded as n. 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 delta (1-m'), a threshold value beta is set, the standard deviations delta and the threshold value beta are compared one by one, the column vector corresponding to delta < beta is deleted, and only the column vector of delta > beta is reserved. Finally m 'column vectors are obtained, and a fused spectrum matrix S' (n, m) after dimensionality reduction is obtained.

The method for establishing the regression model to calculate the relevant parameters mainly comprises the following steps:

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

Multivariate linear regression model:

W＝SK+E

where W is a dependent variable matrix, S is an independent variable matrix, K is a coefficient matrix, and E is an error matrix

With the knowledge of W and S, K and E are obtained through the following matrix operation, and thus a bilirubin prediction model is obtained.

K＝(S'S)^-1S'W

E＝W-SK

Wherein S 'is the transposed matrix of S, (S' S)^-1Represents the inverse matrix of S' S.

The specific details of the above method have been described in detail in the embodiment of the apparatus part, and the details that are not disclosed can be referred to the embodiment of the apparatus part, and thus are not described again.

Finally, it should be noted that: the above embodiments are only used to illustrate the technical solution of the present invention, and not to limit the same; while the invention has been described in detail and with reference to the foregoing embodiments, it will be understood by those skilled in the art that: the technical solutions described in the foregoing embodiments may still be modified, or some or all of the technical features may be equivalently replaced; and the modifications or the substitutions do not make the essence of the corresponding technical solutions depart from the scope of the technical solutions of the embodiments of the present invention. Furthermore, those skilled in the art will appreciate that while some embodiments described herein include some features included in other embodiments, rather than other features, combinations of features of different embodiments are meant to be within the scope of the invention and form different embodiments. For example, in the claims above, any of the claimed embodiments may be used in any combination. The information disclosed in this background section is only for enhancement of understanding of the general background of the invention and should not be taken as an acknowledgement or any form of suggestion that this information forms the prior art already known to a person skilled in the art.

Claims

1. A multispectral fusion percutaneous health index rapid detection device is characterized by comprising a main board, a light source module and a detector which are arranged in a shell, wherein,

2. The device according to claim 1, further comprising a light source lens and a detector lens, wherein the detector lens is sleeved in the light source lens, the light exit channel is defined between the detector lens and the light source lens, and the detector lens is connected to the light guide channel.

3. The device for rapidly detecting the multispectral fusion percutaneous health indicator as claimed in claim 2, wherein a metal cover for realizing optical isolation is further arranged between the light source lens and the detector lens.

4. The device for rapidly detecting the multispectral fusion percutaneous health indicator as claimed in claim 2, wherein a diffusion film for making the incident direction of the monochromatic light become dispersed and uniform, a first diaphragm for selecting the specific angle of the monochromatic light to pass through, and a second diaphragm for selecting the specific angle of the monochromatic light to pass through are sequentially arranged in the detector lens.

5. The device for rapid detection of multispectral fusion transcutaneous health indicator as claimed in claim 4, wherein the first diaphragm is located at the entrance end of the light guiding channel, and the second diaphragm is located at the exit end of the light guiding channel.

6. The device for rapidly detecting the transcutaneous health indicator in the multi-spectral fusion manner of claim 4, further comprising a linear gradient filter, wherein the linear gradient filter is disposed between the second diaphragm and the detector, or disposed between the first diaphragm and the second diaphragm, and a viewing angle field of the linear gradient filter is matched with an emergence angle of the second diaphragm.

7. The device for rapidly detecting the multispectral fusion transcutaneous health indicator as claimed in claim 6, wherein the linear graded filter comprises a plurality of monochromatic wavelength channels which are uniformly distributed and are used for the monochromatic light with different wavelengths to pass through, and a photosensitive array of the detector is arranged corresponding to the monochromatic wavelength channels of the linear graded filter.

8. The device for rapidly detecting the multispectral fusion percutaneous health indicator according to claim 1, wherein the light source module comprises a plurality of light-emitting light sources, each light-emitting light source comprises a substrate, light-emitting chips and a light-reflecting dam arranged around the edge of the substrate, wherein fluorescent powder is filled around the light-emitting chips in part of the light-emitting light sources, and the light-emitting light sources are electrically connected with the main board, so that the plurality of light-emitting chips emit the monochromatic light under the control of the main board.

9. The device for rapidly detecting the multispectral fusion transcutaneous health indicator according to claim 1, wherein the main board comprises an MCU module, a DAC module, a light source driving module, a signal reading module, an ADC module, a temperature measuring module and an interface module, wherein:

10. A method for rapidly detecting a multispectral fusion percutaneous health indicator, which can be applied to the device of any one of claims 1 to 9, and comprises the following steps:

contacting the sensing end of the housing of any one of claims 1-9 with a surface of an object to be sensed;