AGEs concentration detection spectrometer and control method and system thereof

Abstract

The invention discloses an AGES concentration detection spectrometer and a control method and system thereof.The AGES concentration detection spectrometer comprises a probe, a collimating lens, an optical filter, an optical grating, an adapter with an angle, a reflector, a pressure sensor, a focusing lens, a CMOS camera and a support, and the probe adopts an embedded light source and a hollow detection structure; the probe comprises a cooling fin, a multi-wavelength LED light source and an optical filter, the problem that in the AGES concentration detection process, fluorescence signals are affected by optical parameters such as skin color composition, contact pressure and biological tissue, and consequently AGEs concentration detection is inaccurate is solved through spectrograph structure design and a correction algorithm, the probe has the advantages of being ultrahigh in sensitivity and accuracy, simple in structure and convenient to operate, and the application prospect is wide. The fluorescence spectrum of AGEs parameters in a human body can be continuously monitored in a lossless manner.

Description

Technical Field

[0001] This invention relates to the field of spectroscopic analysis instruments, and more particularly to an AGES concentration detection spectrometer and its control method and system. Background Technology

[0002] Advanced glycation end products (AGEs) are a class of complex molecules formed through non-enzymatic reactions. Numerous studies have shown that the accumulation of AGEs can cause inflammation, immune dysfunction, and other problems, contributing to the development and progression of related diseases, including diabetes, kidney disease, cardiovascular disease, and neurological disorders. Currently, methods for detecting AGEs are mainly divided into two categories: biochemical methods and non-destructive optical methods. Biochemical methods involve the collection of blood or urine samples. While biochemical methods offer high detection accuracy, the process is complex. Especially for blood samples, invasive blood collection is required, causing discomfort to the test subjects. This biochemical test is not only costly but also time-consuming, taking 8-9 hours. Developing non-invasive, convenient, and painless detection methods is crucial for the practical and continuous measurement of AGEs in human blood and tissues, and is fundamental for long-term monitoring and research on their role in chronic diseases.

[0003] Optical non-destructive testing methods are implemented by analyzing the autofluorescence properties of advanced glycation end products (AGEs). The main absorption band of AGEs is between 340 nm and 420 nm, while the fluorescence spectrum covers the 420 nm to 600 nm band. Under normal circumstances, the concentration of AGEs fluctuates within a specific range; concentrations exceeding this range require close monitoring of health conditions. For example, the serum AGE concentration in healthy volunteers is 3.3 ± 1.0 mU / ml, while the concentration in patients with non-insulin-dependent diabetes mellitus is 7.2 ± 14.6 mU / ml. Furthermore, elevated AGE concentrations are associated with an increased risk of cardiovascular disease and Alzheimer's disease. Therefore, the application of optical non-destructive testing methods can provide crucial information for the early diagnosis of diseases.

[0004] Existing foreign technologies utilize fiber optic spectrometers for detection, irradiating the skin with a 300-400 nm excitation light source and capturing the signal using a glass fiber optic spectrometer. However, the low efficiency of autofluorescence hinders transdermal detection. In vivo, at relatively low AGE concentrations, the fluorescence peaks of AGEs are significantly weakened by the strong and time-varying autofluorescence of the skin, further exacerbated by shot noise, making the fluorescence of AGEs even weaker. The propagation characteristics of the fluorescence signal are influenced by skin color composition, contact pressure, and the optical parameters of biological tissues. Foreign patents attempt to circumvent the influence of skin color by analyzing tissues such as the retina and wrist, but the fragile structure of the retina is unsuitable for long-term monitoring. Other patents that use calibration models to correct AGE fluorescence signals require prior knowledge of skin type, age, and subject habits. The introduction of additional information necessitates initial data collection, which is detrimental to reducing detection costs. Summary of the Invention

[0005] This application provides an AGES concentration detection spectrometer and its control method and system, which solves the problem that the fluorescence signal is affected by optical parameters such as skin color composition, contact pressure, and biological tissue during the AGES concentration detection process, resulting in inaccurate AGES concentration detection. This application has ultra-high sensitivity and accuracy, and can continuously monitor the fluorescence spectrum of AGES parameters in the human body without damage.

[0006] This application provides an AGES concentration detection spectrometer, including a probe, collimating lens, filter, grating, angled adapter, reflector, pressure sensor, focusing lens, CMOS camera, and bracket. The probe employs an embedded light source and a hollow detection structure. The probe includes a heat sink, a multi-wavelength LED light source, and a filter. The probe has a slit at its center. The probe sequentially emits excitation light of different wavelengths at a 45° angle to irradiate skin tissue, and the skin tissue is then excited to fluoresce, which is transmitted downwards into the slit. The probe contains four of the multi-wavelength LED light sources, three of which are used to excite AGES fluorescence in the human body, and the other is used to correct tissue parameters.

[0007] Preferably, the wavelengths of the multi-wavelength LED light source used to excite AGEs fluorescence in the human body are 365nm, 395nm, and 415nm; the wavelength of the multi-wavelength LED light source used to correct tissue parameters is 520nm.

[0008] Preferably, the filter corresponds to each multi-wavelength LED light source.

[0009] Preferably, the sensor of the CMOS camera is an N*M two-dimensional array, where N represents the horizontal axis pixels and M represents the vertical axis light intensity; the horizontal axis pixels are calibrated to determine the specific wavelength range corresponding to each pixel.

[0010] This application also proposes a control method for an AGES concentration detection spectrometer, including the following steps:

[0011] Step S1: Scan and turn on the camera. Set the exposure time on the host computer and determine the exposure time when the camera acquires the first three fluorescence spectra.

[0012] Step S2: The microcontroller waits for serial port information from the host computer in a loop. When it receives serial port information from the host computer, it compares the information with the preset lighting conditions and lights up the LED light source of the corresponding wavelength.

[0013] Step S3: Obtain pressure data by reading the signal output by the pressure sensor; obtain spectral information by using the pixel data captured by the camera;

[0014] Step S4: Median filtering is used to reduce noise and obtain the autofluorescence spectrum after contact pressure correction.

[0015] Step S5: Correct the effects of different optical absorption and scattering coefficients on the autofluorescence spectrum;

[0016] Step S6: Correct fluorescence crosstalk caused by non-AGEs substances.

[0017] Preferably, step S4 specifically comprises:

[0018] During the autofluorescence spectroscopy detection process, the system relies on an integrated pressure sensor to simultaneously acquire the autofluorescence intensity variation characteristics under different contact pressures, and establishes a power function fitting formula for "contact pressure - fluorescence intensity" to quantify the relationship between contact pressure and detected autofluorescence intensity:

[0019]

[0020] Among them, F λ (P) is a correction function used to quantify the effect of contact pressure on the detected autofluorescence intensity.

[0021] In obtaining clinical autofluorescence spectra I AGEs During the (λ) process, the contact pressure P is obtained in real time, based on the fitting formula of "contact pressure-fluorescence intensity".

[0022] Obtain the autofluorescence spectrum after contact pressure correction:

[0023] I AGEs (λ) / F λ (P)

[0024] Among them, I AGEs(λ) is the uncorrected autofluorescence spectrum, a function of wavelength λ, and the spectral data actually measured during clinical detection.

[0025] Preferably, step S5 specifically comprises:

[0026] The study used a 520nm LED to irradiate the skin, and simultaneously detected the backscattering spectra of the 520nm LED in different individuals. Using this as a benchmark, the effects of different optical absorption and scattering coefficients on the autofluorescence spectrum were corrected. The 520nm backscattering spectra, corrected for contact pressure, were then standardized. The standardized AGEs fluorescence intensity is expressed as follows:

[0027]

[0028] Preferably, step S6 specifically comprises:

[0029] Discrete three-dimensional fluorescence spectra are obtained by combining three excitation wavelengths, and the data structure is defined as follows:

[0030] A j I AGE s (λ)+B j I AGE s (λ)+C j I AGE s (λ)

[0031] Where A j B j C j The values ​​represent the product of the quantum efficiency and concentration of the three autofluorescent substances under the j-th wavelength. The discrete coefficients are linearly optimized using Bayesian optimization techniques, with the AGEs concentration test value of the corresponding volunteers' blood or urine as a constraint condition, to mathematically cancel the fluorescence crosstalk generated by non-AGEs substances.

[0032] This application also proposes a control system for an AGES concentration detection spectrometer, comprising:

[0033] The exposure control module sets the exposure time via a host computer, determining the exposure time when the camera acquires the first three fluorescence spectra.

[0034] The light source control module uses a microcontroller to continuously wait for serial port information from the host computer. When it receives serial port information from the host computer, it compares the information with the preset lighting conditions and lights up the LED light source of the corresponding wavelength.

[0035] The information output module acquires pressure data by reading the signal output by the pressure sensor and obtains spectral information by acquiring pixel data captured by the camera.

[0036] The pressure correction module uses median filtering to reduce noise and obtains the autofluorescence spectrum after contact pressure correction.

[0037] Skin color correction module, used to correct the effects of different optical absorption and scattering coefficients on the autofluorescence spectrum;

[0038] The non-AGEs correction module is used to correct fluorescence crosstalk caused by non-AGEs substances.

[0039] One or more technical solutions provided in the embodiments of this application have at least the following technical effects or advantages:

[0040] 1. Since the probe adopts an embedded light source and a hollow detection structure, based on the basic structure of the spectral detection system, and using the hollow detector and its close proximity to the surface of biological tissue, a "direct contact" biological tissue spectral detection method is proposed to improve the sensitivity of the test and enable non-destructive and continuous monitoring of the fluorescence spectrum of AGEs parameters in the human body.

[0041] 2. A slit is set at the very center of the probe. During detection, the entire slit can collect fluorescence from the skin. The autofluorescence generated by biological tissue under the action of excitation light can directly pass through the slit and enter the imaging spectrometer, which greatly improves the collection efficiency compared with traditional fiber optic detection.

[0042] 3. The probe of this application uses four wavelength LED light sources, one of which is a reflected light source used to calibrate the interference of different human tissue optical parameters on fluorescence signals, thereby improving the accuracy of detection.

[0043] 4. The control algorithm of this application also includes three data processing steps: pressure correction, skin color correction, and non-AGEs substance correction. By designing the mechanical structure and using the pressure correction method, a pressure sensor is placed in the system to obtain the current pressure under the skin while collecting human AGEs fluorescence, thus eliminating the interference of pressure on the fluorescence signal. The influence of different optical absorption and scattering coefficients on the autofluorescence spectrum is eliminated through spectral normalization processing. The discrete coefficients are linearly optimized and combined using Bayesian optimization technology to counteract fluorescence crosstalk caused by non-AGEs substances. Attached Figure Description

[0044] Figure 1 This is a schematic diagram of the spectrometer in Embodiment 1 of this application;

[0045] Figure 2 This is a schematic diagram of the spectrometer probe in Embodiment 1 of this application;

[0046] Figure 3 This is the optical path diagram of the spectrometer probe in Embodiment 1 of this application;

[0047] Figure 4 This is a flowchart of the spectrometer control method in Embodiment 2 of this application;

[0048] In the diagram: 1. Probe; 2. Collimating lens; 3. Filter; 4. Grating; 5. Angular adapter; 6. Mirror; 7. Pressure sensor; 8. Focusing lens; 9. CMOS camera; 10. Bracket; 201. Heat sink; 202. Multi-wavelength LED light source; 203. Filter. Detailed Implementation

[0049] This application provides an AGEs concentration detection spectrometer and its control method, solving the problem of inaccurate AGEs concentration detection caused by the influence of optical parameters such as skin color composition, contact pressure, and biological tissue on the fluorescence signal during AGEs concentration detection. This application features ultra-high sensitivity and accuracy, enabling non-destructive and continuous monitoring of the fluorescence spectrum of AGEs parameters in the human body. To better understand the above technical solution, a detailed description will be provided below with reference to the accompanying drawings and specific embodiments.

[0050] Example 1

[0051] like Figure 1 As shown, the present invention is an AGES concentration detection spectrometer comprising: a probe 1, a collimating lens 2, a filter 3, a grating 4, an angled adapter 5, a reflector 6, a pressure sensor 7, a focusing lens 8, a CMOS camera 9, and a bracket 10.

[0052] like Figure 2 As shown, probe 1 employs an embedded light source and a hollow detection structure. The light source detection structure includes a heat sink 201, a multi-wavelength LED light source 202, and a filter 203. Probe 1 has a slit at its center, allowing the entire slit to collect fluorescence from the skin during detection, significantly improving collection efficiency compared to traditional fiber optic detection. Four multi-wavelength LED light sources 202 are evenly distributed around the probe; three are 365nm, 395nm, and 415nm respectively to excite AGEs fluorescence in the human body, and the remaining one is 520nm for correcting tissue parameters. The filter 3 corresponds to each multi-wavelength LED light source 202; for example, if the light source is 365nm, then a 365nm bandpass filter is used.

[0053] Detection optical path such as Figure 3 As shown, the probe's LED sequentially emits excitation light of different wavelengths (365nm, 395nm, and 415nm) to irradiate the skin tissue at a 45° angle. The skin tissue is then excited to emit fluorescence, which is transmitted downwards into the slit and subsequently into the fluorescence spectrometer.

[0054] During detection, the skin is placed above probe 1. Excited by the light source in probe 1, the AGEs in the skin emit fluorescence that enters probe 1. This fluorescence is then collimated into parallel light by collimating lens 2 and passes through a long-pass filter 3. Under the action of transmission grating 4, the incoming fluorescence is dispersed and transmitted forward through reflecting mirror 6. Finally, it is focused onto CMOS camera 9 by focusing lens 8.

[0055] During detection, the skin is compressed due to the reaction force of the probe. Fluorescence emission from the skin is also affected by pressure, so the pressure needs to be controlled during each detection. This invention uses a pressure sensor 7 to collect the pressure, which is mounted on a 3D-printed support 10.

[0056] Example 2

[0057] like Figure 3 As shown, this embodiment provides a control method for the aforementioned spectrometer. After the host computer cyclically sends serial port information to light the corresponding LED, it waits 100ms for information transmission and microcontroller processing before capturing fluorescence data and reading it from the data acquisition card. Finally, the acquired fluorescence spectrum and contact pressure value are saved. The exposure time can be set before the cycle to determine the exposure time for the camera to acquire the first three fluorescence spectra. The method includes the following steps:

[0058] Step S1: Scan and turn on the camera. Set the exposure time on the host computer to determine the exposure time when the camera acquires the first three fluorescence spectra.

[0059] The exposure time is set via the host computer: 1000ms for LEDs at 365nm, 395nm, and 415nm, and 100ms for LEDs at 520nm.

[0060] In step S2, the microcontroller waits for serial port information from the host computer. When it receives serial port information from the host computer, it compares the information with the preset lighting conditions and lights up the LED light source of the corresponding wavelength.

[0061] Before the camera captures the fluorescence signal, an LED lighting operation should be performed. At this time, the host computer connects to the STM32 microcontroller, allowing it to send different LED lighting commands via serial port. Upon receiving the serial port information, the microcontroller processes and analyzes it, thus lighting the corresponding wavelength LED. The STM32 microcontroller's functionality is written and programmed using C language on Keil 5 software. The microcontroller's main logic is to continuously wait for serial port information from the host computer. When a serial port message is received, it is compared with the pre-set lighting conditions to ensure that the corresponding LED is lit. Therefore, this operation guarantees that the LEDs are lit or turned off as expected. The main logic of the microcontroller is as follows: When the microcontroller receives a serial port signal from the host computer, the Uart_Getflag function returns 1, thus obtaining the serial port information from the host computer. Then, the program enters the discrimination stage. At this time, "LED1", "LED2", "LED3", and "LED4" are set as the lighting strings corresponding to 365nm, 395nm, 415nm, and 520nm LEDs, respectively. After comparing the strings, the corresponding wavelength LED can be lit. The serial port parameters are set to a baud rate of 115200, no parity bit, 8 data bits, and 1 stop bit. The LED lighting time is set to 1.5 seconds in the microcontroller. This design ensures sufficient time to capture the fluorescence signal during the LED lighting period.

[0062] Step S3: Obtain pressure data by reading the signal output by the pressure sensor; obtain spectral information by obtaining pixel data captured by the camera.

[0063] While each LED is lit, the host computer reads and saves the data output by the pressure sensor module. For each LED band, three pressure sensor module output values ​​are saved. Averaging these values ​​and converting them into a pressure value represents the contact pressure applied by the subject to the system during that specific LED detection.

[0064] A slit-grating spectrometer disperses incident light by passing it through a slit and then through a grating, causing different wavelengths of light to appear at different positions on the camera's sensor. The camera's sensor is typically an N*M two-dimensional array, where N represents the number of pixels on the horizontal axis. By calibrating these horizontal axis pixels, a specific wavelength range can be determined for each pixel; therefore, each horizontal axis pixel on the sensor corresponds to a wavelength range. The vertical axis pixels reflect the light intensity distribution. By reading and processing these pixel signals, a spectrum is generated where the horizontal axis represents wavelength and the vertical axis represents light intensity. In this way, the pixel data captured by the camera, after processing, yields complete spectral information.

[0065] Step S4: Median filtering is used to reduce noise and obtain the autofluorescence spectrum after contact pressure correction.

[0066] After obtaining the spectral information, the raw spectral data is first preprocessed. Since the raw fluorescence spectra obtained after subjects are excited by excitation light under different pressures have significant noise, median filtering can be used to reduce the noise.

[0067] During the autofluorescence spectroscopy detection process, the system relies on an integrated pressure sensor to synchronously acquire the autofluorescence intensity variation characteristics under different contact pressures, and establishes a power function fitting formula of "contact pressure-fluorescence intensity" to quantify the relationship between contact pressure and detected autofluorescence intensity.

[0068]

[0069] in, This is the autofluorescence intensity under contact pressure P; autofluorescence intensity is a quantity measured in spectroscopy, usually expressed as a function of wavelength. F λ (P) This is a correction function used to quantify the effect of contact pressure on the detected autofluorescence intensity. This function shows the relationship between contact pressure and fluorescence intensity, derived through an experimental model.

[0070] In obtaining clinical autofluorescence spectra I AGEs During the (λ) process, the contact pressure P is obtained in real time, based on the fitting formula of "contact pressure-fluorescence intensity".

[0071] The autofluorescence spectrum was obtained after contact pressure correction, which accounted for the effect of contact pressure on fluorescence intensity. This ratio allows for more accurate fluorescence spectral information, eliminating errors introduced by contact pressure.

[0072] I AGEs (λ) / F λ (P)

[0073] Among them, I AGEs (λ) is the uncorrected autofluorescence spectrum, a function of wavelength λ, and is the spectral data actually measured during clinical detection.

[0074] Step S5: Correct the effects of different optical absorption and scattering coefficients on the autofluorescence spectrum.

[0075] Because different individuals have different skin colors, their optical absorption and scattering coefficients also differ. Therefore, this invention incorporates the use of a 520nm LED to irradiate the skin, while simultaneously detecting the backscattering spectrum of the 520nm LED for different individuals. This data serves as a benchmark to correct for the influence of different optical absorption and scattering coefficients on the autofluorescence spectrum.

[0076] The backscattering spectrum at 520 nm, corrected for contact pressure, was normalized. Therefore, the final normalized AGEs fluorescence intensity can be expressed as:

[0077]

[0078] Step S6: Correct fluorescence crosstalk caused by non-AGEs substances.

[0079] When AGEs are excited to produce autofluorescence, fluorescence crosstalk occurs because other substances in skin tissue within the 420nm-600nm range, such as collagen and NADH, are also excited. To extract the main fluorescent components of AGEs, this invention proposes to combine three excitation wavelengths to obtain discrete three-dimensional fluorescence spectra, with the data structure defined as follows: A j I AGE s (λ)+B j I AGE s (λ)+C j I AGE s (λ), where A j B j C j These represent the product of the quantum efficiency and concentration of the three autofluorescent substances under the j-th wavelength. A linear optimization of the discrete coefficients is performed using Bayesian optimization techniques, with the AGEs concentration test values ​​from the blood or urine of the corresponding volunteers as constraints. This mathematically cancels fluorescence crosstalk caused by non-AGEs substances, specifically including:

[0080] Step S61: Standardize the fluorescence intensity at different wavelengths, output the standard spectrum, obtain the combined fluorescence spectrum at each excitation wavelength, and add these component spectra together to obtain the total mixed fluorescence spectrum;

[0081] Step S62: Define the optimization objective function and the error value calculation formula;

[0082] Step S63: Use an optimization algorithm to find the optimal coefficients and minimum distance to minimize the deviation between the modeled fluorescence spectrum and the observed fluorescence spectrum;

[0083] Step S64: Calculate the final result. Calculate the final AGEs estimate using the optimal coefficients obtained from optimization, and calculate the correlation coefficient between the estimate and the actual AGEs value.

[0084] Example 3

[0085] This embodiment provides a control system for the above-mentioned spectrometer, including:

[0086] The exposure control module sets the exposure time via a host computer, determining the exposure time for the camera to acquire the first three fluorescence spectra.

[0087] The light source control module uses a microcontroller to continuously wait for serial port information from the host computer. When it receives serial port information from the host computer, it compares the information with the preset lighting conditions and lights up the LED light source of the corresponding wavelength.

[0088] The information output module acquires pressure data by reading the signal output by the pressure sensor and obtains spectral information by acquiring pixel data captured by the camera.

[0089] The pressure correction module uses median filtering to reduce noise and obtain the autofluorescence spectrum after contact pressure correction.

[0090] The skin color correction module is used to correct the effects of different optical absorption and scattering coefficients on the autofluorescence spectrum.

[0091] The non-AGEs correction module is used to correct fluorescence crosstalk caused by non-AGEs substances.

[0092] The embodiments described herein are preferred embodiments of the present invention and are not intended to limit the scope of protection of the present invention. Therefore, all equivalent changes made in accordance with the structure, shape, and principle of the present invention should be covered within the scope of protection of the present invention.

[0093] Although preferred embodiments of the invention have been described, those skilled in the art, upon learning the basic inventive concept, can make other changes and modifications to these embodiments. Therefore, the appended claims are intended to be interpreted as including both the preferred embodiments and all changes and modifications falling within the scope of the invention.

[0094] Obviously, those skilled in the art can make various modifications and variations to this invention without departing from its spirit and scope. Therefore, if these modifications and variations fall within the scope of the claims of this invention and their equivalents, this invention also intends to include these modifications and variations.

Claims

1. An AGES concentration detection spectrometer, comprising a probe, a collimating lens, a filter, a grating, an angled adapter, a reflector, a pressure sensor, a focusing lens, a CMOS camera, and a support, characterized in that, The probe employs an embedded light source and a hollow detection structure. The probe includes a heat sink, a multi-wavelength LED light source, and a filter. The probe has a slit in the center. The probe sequentially emits excitation light of different wavelengths at a 45° angle to irradiate the skin tissue. The skin tissue is then excited to fluoresce, which is transmitted downwards into the slit. The probe contains four of the multi-wavelength LED light sources, three of which are used to excite AGEs fluorescence in the human body, and the other is used to correct tissue parameters.

2. The spectrometer as described in claim 1, characterized in that, The wavelengths of the multi-wavelength LED light source used to excite AGEs fluorescence in the human body are 365nm, 395nm, and 415nm; the wavelength of the multi-wavelength LED light source used to correct tissue parameters is 520nm.

3. The spectrometer as described in claim 1, characterized in that, The filter corresponds to each multi-wavelength LED light source.

4. The spectrometer as described in claim 1, characterized in that, The sensor of the CMOS camera is an N*M two-dimensional array, where N represents the horizontal axis pixels and M represents the vertical axis light intensity; the horizontal axis pixels are calibrated to determine the specific wavelength range corresponding to each pixel.

5. A control method for an AGES concentration detection spectrometer, characterized in that, Includes the following steps: Step S1: Scan and turn on the camera. Set the exposure time on the host computer and determine the exposure time when the camera acquires the first three fluorescence spectra. Step S2: The microcontroller waits for serial port information from the host computer in a loop. When it receives serial port information from the host computer, it compares the information with the preset lighting conditions and lights up the LED light source of the corresponding wavelength. Step S3: Obtain pressure data by reading the signal output by the pressure sensor; obtain spectral information by using the pixel data captured by the camera; Step S4: Median filtering is used to reduce noise and obtain the autofluorescence spectrum after contact pressure correction. Step S5: Correct the effects of different optical absorption and scattering coefficients on the autofluorescence spectrum; Step S6: Correct fluorescence crosstalk caused by non-AGEs substances.

6. The control method for the spectrometer as described in claim 5, characterized in that, Step S4 specifically involves: During the autofluorescence spectroscopy detection process, the system relies on an integrated pressure sensor to synchronously acquire the autofluorescence intensity variation characteristics under different contact pressures, and establishes a power function fitting formula for "contact pressure - fluorescence intensity" to quantify the relationship between contact pressure and detected autofluorescence intensity: where F λ (P) is a correction function that quantifies the effect of contact pressure on the detected autofluorescence intensity. In acquiring clinical autofluorescence spectrum I AGEs (λ) In the process, the real-time acquisition of contact pressure P, based on the "contact pressure-fluorescence intensity" fitting formula; Obtain the autofluorescence spectrum after contact pressure correction: I AGEs (λ) / F λ (P) Among them, I AGEs (λ) is the uncorrected autofluorescence spectrum, a function of wavelength λ, and the spectral data actually measured during clinical detection.

7. The control method for the spectrometer as described in claim 5, characterized in that, Step S5 specifically involves: The study used a 520nm LED to irradiate the skin, and simultaneously detected the backscattering spectra of the 520nm LED in different individuals. Using this as a benchmark, the effects of different optical absorption and scattering coefficients on the autofluorescence spectrum were corrected. The 520nm backscattering spectra, corrected for contact pressure, were then standardized. The standardized AGEs fluorescence intensity is expressed as follows:

8. The control method for a spectrometer as described in claim 5, characterized in that, Step S6 specifically involves: Discrete three-dimensional fluorescence spectra are obtained by combining three excitation wavelengths, and the data structure is defined as follows: A j I AGEs (l)+B j I AGEs (λ)+C j I AGEs (l) Where A j B j C j The values ​​represent the product of the quantum efficiency and concentration of the three autofluorescent substances under the j-th wavelength. The discrete coefficients are linearly optimized using Bayesian optimization techniques, with the AGEs concentration test value of the corresponding volunteers' blood or urine as a constraint condition, to mathematically cancel the fluorescence crosstalk generated by non-AGEs substances.

9. A control system for an AGES concentration detection spectrometer, characterized in that, include: The exposure control module sets the exposure time via a host computer, determining the exposure time when the camera acquires the first three fluorescence spectra. The light source control module uses a microcontroller to continuously wait for serial port information from the host computer. When it receives serial port information from the host computer, it compares the information with the preset lighting conditions and lights up the LED light source of the corresponding wavelength. The information output module acquires pressure data by reading the signal output by the pressure sensor and obtains spectral information by acquiring pixel data captured by the camera. The pressure correction module uses median filtering to reduce noise and obtains the autofluorescence spectrum after contact pressure correction. Skin color correction module, used to correct the effects of different optical absorption and scattering coefficients on the autofluorescence spectrum; The non-AGEs correction module is used to correct fluorescence crosstalk caused by non-AGEs substances.

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