Patch type noninvasive continuous blood glucose detector and blood glucose measuring and calculating method

Abstract

The invention belongs to the technical field of medical equipment, and particularly relates to a patch type noninvasive continuous blood glucose detector and a blood glucose measuring and calculating method.When the patch type noninvasive continuous blood glucose detector is used, the patch type noninvasive continuous blood glucose detector is fixed to the body surface of a living body through a fixing unit; photoplethysmography signals of a measured organism, contact heat of the measured organism, radiant heat of the measured organism and temperature and humidity around the measured organism are collected through the signal collecting and processing unit, and then the collected organism information data are processed through the signal collecting and processing unit. Therefore, the blood sugar concentration of the measured living body is predicted; the device is small in size, is attached to the skin of an organism during use, is convenient to carry, has no injury to the organism during detection, has no consumption of consumables, saves the cost, can continuously detect the blood glucose of the organism, and is convenient for the organism to know the blood glucose condition at any time.

Description

Technical Field

[0001] The present invention belongs to the technical field of medical equipment, and in particular relates to a patch-type non-invasive continuous blood glucose detector and a blood glucose measurement method. Background Art

[0002] As a chronic endocrine metabolic disease that cannot be cured by current medical means, the effective management of diabetes is highly dependent on frequent monitoring of blood glucose concentrations to adjust treatment. The current mainstream detection methods: venous blood drawing and fingertip capillary puncture blood collection both have limitations. These methods are inherently traumatic, and repeated punctures not only cause continuous pain and psychological burden to patients, but also increase the risk of potential infection. At the same time, each test requires disposable consumables such as test strips and blood collection needles. The equipment required for testing (such as blood glucose meters) is usually large in size and weight, and is not portable enough, which limits the patient's daily activities. The most critical thing is that the above methods are all discrete, non-continuous single-point measurements, which cannot provide dynamic, real-time information on blood glucose changes. Patients cannot understand their blood glucose status anytime and anywhere in their daily lives, and the existing methods are relatively expensive.

[0003] Therefore, a patch-type non-invasive continuous blood glucose monitor and a blood glucose measurement method are proposed. Summary of the Invention

[0004] The purpose of the present invention is to provide a patch-type non-invasive continuous blood glucose monitor and a blood glucose measurement method to solve the above problems.

[0005] To achieve the above object, the present invention provides the following solutions:

[0006] A patch-type non-invasive continuous blood glucose monitor, comprising:

[0007] shell;

[0008] a signal acquisition and processing unit, disposed in the housing, for acquiring biological information data and processing the acquired data to predict blood glucose concentration;

[0009] a power management unit, disposed in the housing, and configured to provide energy to the signal acquisition and processing unit;

[0010] a fixing unit, disposed on the housing, and configured to fix the housing on a biological body;

[0011] The biological information data collected by the signal collection and processing unit includes at least the photoplethysmographic signal of the measured biological body, the contact heat of the measured biological body, the radiant heat of the measured biological body, and the temperature and humidity around the measured biological body.

[0012] Preferably, the housing comprises:

[0013] A shell having a cavity coaxially defined therein, and an opening defined at one end of the shell, the opening being in communication with the cavity;

[0014] a bottom cover, disposed at the opening, with a through slot formed on the bottom cover, the through slot being in communication with the cavity;

[0015] A first through hole is provided on the outer side wall of the shell;

[0016] At least one protrusion is provided on the side wall of the cavity, and the protrusion is provided along the length direction of the shell.

[0017] Preferably, the signal acquisition and processing unit includes:

[0018] A circuit board is fixedly mounted in the cavity, and a groove adapted to fit the protrusion is formed at an outer edge of the circuit board;

[0019] A signal acquisition module is fixedly mounted on the circuit board, the signal acquisition module is arranged corresponding to the through slot, and the signal acquisition module is used to collect biological information data;

[0020] a signal processing module fixedly mounted on the circuit board, the signal processing module being electrically connected to the signal acquisition module, and configured to process the biological information data collected by the signal acquisition module to predict the blood glucose concentration;

[0021] A Bluetooth module is fixedly mounted on the circuit board, the Bluetooth module is electrically connected to the signal processing module, and is used to transmit the blood glucose concentration predicted by the signal processing module to a receiving device.

[0022] Preferably, the power management unit includes:

[0023] a battery holder, fixedly mounted on the circuit board, the battery holder being electrically connected to the signal acquisition module, the signal processing module, and the Bluetooth module, the battery holder being electrically connected to a charging cable, a charging interface of the charging cable being disposed within the first through hole;

[0024] A battery, detachably connected to the battery holder, the battery providing energy to the signal acquisition module, the signal processing module and the Bluetooth module through the battery holder;

[0025] A power switch is provided on the housing, and is used to disconnect or connect the battery holder with the signal acquisition module, the signal processing module, and the Bluetooth module.

[0026] Preferably, the fixing unit includes:

[0027] a fixing block, detachably connected to the bottom cover;

[0028] An adhesive tape is arranged on a side of the fixing block away from the bottom cover, and the adhesive tape is used for adhering to a biological body.

[0029] A blood glucose measurement method based on the patch-type non-invasive continuous blood glucose monitor comprises the following steps:

[0030] Acquiring biological information data through a signal acquisition and processing unit, the biological information data including at least a photoplethysmographic signal of the measured biological body, contact heat of the measured biological body, radiant heat of the measured biological body, and temperature and humidity around the measured biological body;

[0031] Based on a preset algorithm, the blood oxygen saturation of the measured organism is calculated based on the photoplethysmography signal of the measured organism, the blood flow velocity of the measured organism is calculated based on the photoplethysmography periodic signal of the measured organism, and the local metabolic rate of the measured organism is calculated based on the contact heat of the measured organism, the radiant heat of the measured organism, and the temperature and humidity around the measured organism;

[0032] The calculated blood oxygen saturation, blood flow rate and local metabolic rate of the measured organism are input into a preset model to predict the final blood glucose concentration.

[0033] Preferably, the calculation formula for the blood oxygen saturation of the measured organism is:

[0034]

[0035] Among them, SpO2 is the blood oxygen saturation of the measured organism, a and b are calibration coefficients, AC 660 The range of 660nm red light photoplethysmography, DC 660 is the average value of 660nm red light photoplethysmography, AC 880 The range of the photoplethysmography of the 880nm near-infrared light is DC 880 It is the average value of the 880nm near-infrared light photoplethysmography.

[0036] Preferably, the calculation formula of the blood flow rate of the measured organism is:

[0037]

[0038] Wherein, BV is the blood flow velocity of the measured organism, c and d are calibration coefficients, T is the photoplethysmographic period, K is the pulse waveform characteristic, and S is the blood vessel cross-sectional area.

[0039] Preferably, the calculation formula for the local metabolic rate of the measured organism is:

[0040] BMR=W con +W eva +W rad ,

[0041] Where BMR is the local metabolic rate of the organism being measured, W con is the convection heat, W eva is the heat of vaporization, W rad It is metabolic heat.

[0042] Preferably, the calculation formula for convection heat is:

[0043] W con =h×(t p -t e ),

[0044] Where h is the convective heat transfer coefficient, t p is the surface temperature of the measured organism, t e is the ambient temperature of the measured organism.

[0045] Compared with the prior art, the present invention has the following advantages and technical effects:

[0046] When in use, the patch-type non-invasive continuous blood glucose monitor of the present invention is fixed to the surface of a living body via a fixing unit, and the signal acquisition and processing unit collects the photoplethysmographic signal of the measured living body, the contact heat of the measured living body, the radiant heat of the measured living body, and the temperature and humidity around the measured living body. The signal acquisition and processing unit then processes the collected biological information data to predict the blood glucose concentration of the measured living body.

[0047] The device of the present invention is small in size and can be attached to the skin of a living body when in use, making it easy to carry. During testing, it does not cause any trauma to the living body and there is no loss of consumables, thus saving costs. It can also continuously test the blood sugar of the living body, making it easy for the living body to understand its blood sugar status at any time. BRIEF DESCRIPTION OF THE DRAWINGS

[0048] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the embodiments. Obviously, the drawings described below are only some embodiments of the present invention. Those skilled in the art can also derive other drawings based on these drawings without inventive work.

[0049] Figure 1 It is an overall view of the present invention;

[0050] Figure 2 Schematic diagram of the structure of the housing in the present invention;

[0051] Figure 3 It is a schematic diagram of the overall structure of the present invention;

[0052] Figure 4 This is a flow chart for calculating blood glucose concentration according to the present invention;

[0053] Among them, 1. Shell; 11. Power switch; 12. Through hole 1; 13. Protrusion; 14. Bottom cover; 2. Power management unit; 21. Battery; 22. Battery holder; 3. Signal acquisition and processing unit; 31. Signal acquisition module; 32. Signal processing module; 33. Bluetooth module; 4. Fixing unit; 41. Fixing block; 42. Adhesive tape. DETAILED DESCRIPTION

[0054] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of the present invention.

[0055] In order to make the above-mentioned objects, features and advantages of the present invention more obvious and easy to understand, the present invention is further described in detail below with reference to the accompanying drawings and specific embodiments.

[0056] Reference Figures 1 to 3 The present invention discloses a patch-type non-invasive continuous blood glucose monitor, comprising:

[0057] Shell 1;

[0058] The signal acquisition and processing unit 3 is provided in the housing 1 and is used to collect biological information data and process the collected data to predict the blood glucose concentration;

[0059] A power management unit 2 is provided in the housing 1 and is used to provide energy to the signal acquisition and processing unit 3;

[0060] A fixing unit 4 is provided on the housing 1 and is used to fix the housing 1 on the organism;

[0061] The biological information data collected by the signal collection and processing unit 3 includes at least the photoplethysmographic signal of the measured biological body, the contact heat of the measured biological body, the radiant heat of the measured biological body, and the temperature and humidity around the measured biological body.

[0062] Further optimizing the solution, the housing 1 includes:

[0063] The shell has a cavity coaxially defined therein, and an opening is defined at one end of the shell, the opening being in communication with the cavity;

[0064] A bottom cover 14 is provided at the opening, and a through slot is formed on the bottom cover 14, the through slot being in communication with the cavity;

[0065] A through hole 12 is provided on the outer wall of the housing;

[0066] At least one protrusion 13 is provided on the side wall of the cavity, and the protrusion 13 is provided along the length direction of the shell.

[0067] Further optimizing the solution, the signal acquisition and processing unit 3 includes:

[0068] The circuit board is fixedly installed in the cavity, and a groove adapted to the protrusion 13 is provided at the outer edge of the circuit board;

[0069] A signal acquisition module 31 is fixedly mounted on the circuit board. The signal acquisition module 31 is arranged corresponding to the through slot and is used to collect biological information data.

[0070] The signal acquisition module 31 includes at least a thermal radiation temperature sensor, an ambient temperature and humidity sensor, and a reflective photoplethysmography sensor, which respectively collects the photoplethysmography signal of the measured biological subject, the contact heat of the measured biological subject, the radiant heat of the measured biological subject, and the temperature and humidity around the measured biological subject;

[0071] The signal acquisition module 31 is fixed in the through slot of the bottom cover 14. The distance between the probe of each sensor of the signal acquisition module 31 and the skin is 3-5mm. This distance is the optimal detection distance of the sensor and has higher measurement accuracy.

[0072] The signal processing module 32 is fixedly mounted on the circuit board and is electrically connected to the signal acquisition module 31. The signal processing module 32 is used to process the biological information data collected by the signal acquisition module 31 to predict the blood glucose concentration;

[0073] The signal processing module 32 uses stm32f103c8t6 as the main control chip to filter the signal transmitted from the data acquisition module 31 to reduce the impact of environmental and equipment light noise on the detection results;

[0074] A Bluetooth module 33 is fixedly mounted on the circuit board. The Bluetooth module 33 is electrically connected to the signal processing module 32 and is used to transmit the blood glucose concentration predicted by the signal processing module 32 to a receiving device.

[0075] The Bluetooth module 33 uses the ECB02 module to send the blood glucose value and battery power calculated by the signal processing module 32 to the mobile device, facilitating long-term recording and continuous monitoring of blood glucose.

[0076] To further optimize the solution, the power management unit 2 includes:

[0077] The battery holder 22 is fixedly mounted on the circuit board. The battery holder 22 is electrically connected to the signal acquisition module 31, the signal processing module 32, and the Bluetooth module 33. The battery holder 22 is electrically connected to a charging cable, and the charging interface of the charging cable is disposed in the through hole 12.

[0078] The battery 21 is detachably connected to the battery holder 22 , and the battery 21 provides energy to the signal acquisition module 31 , the signal processing module 32 , and the Bluetooth module 33 through the battery holder 22 ;

[0079] The power switch 11 is provided on the housing 1 , and is used to disconnect or connect the battery holder 22 with the signal acquisition module 31 , the signal processing module 32 and the Bluetooth module 33 .

[0080] Further optimizing the solution, the fixing unit 4 includes:

[0081] The fixing block 41 is detachably connected to the bottom cover 14;

[0082] The adhesive tape 42 is provided on a side of the fixing block 41 away from the bottom cover 14 , and is used for adhering to a biological body.

[0083] Two connecting ears are fixedly connected to the top surface of the fixing block 41. The two connecting ears are arranged opposite to each other. A card slot is opened on the opposite side of the two connecting ears. The outer edge of the bottom cover 14 is clamped in the two card slots to achieve the connection between the fixing block 41 and the bottom cover 14;

[0084] The connecting ears are flexible, making it easy to remove the bottom cover 14;

[0085] The adhesive tape 42 is a patch made of PE film medical tape.

[0086] Reference Figure 4 A blood glucose measurement method based on a patch-type non-invasive continuous blood glucose monitor comprises the following steps:

[0087] Acquiring biological information data through the signal acquisition and processing unit 3, the biological information data at least including the photoplethysmographic signal of the measured biological body, the contact heat of the measured biological body, the radiant heat of the measured biological body, and the temperature and humidity around the measured biological body;

[0088] Based on a preset algorithm, the blood oxygen saturation of the measured organism is calculated based on the photoplethysmography signal of the measured organism, the blood flow velocity of the measured organism is calculated based on the photoplethysmography periodic signal of the measured organism, and the local metabolic rate of the measured organism is calculated based on the contact heat of the measured organism, the radiant heat of the measured organism, and the temperature and humidity around the measured organism;

[0089] The calculated blood oxygen saturation, blood flow rate and local metabolic rate of the measured organism are input into a preset model to predict the final blood glucose concentration.

[0090] Further optimizing the scheme, the calculation formula of the blood oxygen saturation of the measured organism is:

[0091]

[0092] SpO2=(ab×R)×100%,

[0093] Among them, SpO2 is the blood oxygen saturation of the measured organism, a and b are calibration coefficients, AC 660 The range of 660nm red light photoplethysmography, DC 660 is the average value of 660nm red light photoplethysmography, AC 880 The range of the photoplethysmography of the 880nm near-infrared light is DC 880 It is the average value of the 880nm near-infrared light photoplethysmography.

[0094] Among them, a is approximately 104, b is approximately 17;

[0095] Further optimizing the scheme, the calculation formula of the blood flow rate of the measured organism is:

[0096]

[0097] Wherein, BV is the blood flow velocity of the measured organism, c and d are calibration coefficients, T is the photoplethysmographic period, K is the pulse waveform characteristic, which is generally taken as 1 / 3 in clinical practice, and S is the cross-sectional area of ​​the blood vessel, which is taken as a constant of 500.

[0098] Further optimizing the scheme, the calculation formula of the local metabolic rate of the measured organism is:

[0099] BMR=W con +W eva +W rad ,

[0100] Where BMR is the local metabolic rate of the organism being measured, W con is the convection heat, W eva is the heat of vaporization, W rad It is metabolic heat.

[0101] Further optimizing the scheme, the calculation formula of convection heat is:

[0102] W con =h×(t p -t e ),

[0103] Where h is the convective heat transfer coefficient, t p is the surface temperature of the measured organism, t e is the ambient temperature of the measured organism.

[0104] Further optimizing the scheme, the calculation formula of evaporation heat is:

[0105] W eva =HK p (P p -P e ),

[0106] Where H is the heat of vaporization of water, K p is the skin permeability coefficient, P p is the saturated partial pressure of water vapor in the air at skin temperature and humidity, P e It is the saturated partial pressure of water vapor in the air at the actual ambient temperature and humidity.

[0107] To further optimize the scheme, the calculation formula of metabolic heat is:

[0108] W rad =εσt p 4 ,

[0109] Among them, ε is the blackness of the measured skin, and σ is the blackbody radiation constant.

[0110] Specific usage:

[0111] First, attach the blood glucose meter to the patient's test area using the adhesive tape 42. Then, connect the battery holder 22 to the signal acquisition module 31, the signal processing module 32, and the Bluetooth module 33 through the power switch 11. The battery 21 provides energy to the signal acquisition module 31, the signal processing module 32, and the Bluetooth module 33, and the meter starts working.

[0112] During operation, the signal acquisition module 31 collects biological information data, which includes at least the photoelectric volume pulse wave signal of the measured biological body, the contact heat of the measured biological body, the radiant heat of the measured biological body, and the temperature and humidity around the measured biological body;

[0113] The signal processing module 32 processes the biological information data collected by the signal collection module 31. The processing process is as follows:

[0114] For the photoplethysmography signal of the measured organism, referring to the photoplethysmography method, since blood with different oxygen contents absorbs 880nm near-infrared light and 660nm red light to different degrees, the blood oxygen saturation of the measured organism can be obtained according to the Lambert-Beer theorem. The formula is as follows:

[0115]

[0116] SpO2=(ab×R)×100%,

[0117] Among them, SpO2 is the blood oxygen saturation of the measured organism, a and b are calibration coefficients, AC 660 The range of 660nm red light photoplethysmography, DC 660 is the average value of 660nm red light photoplethysmography, AC 880 The range of the photoplethysmography of the 880nm near-infrared light is DC 880 is the mean value of the 880nm near-infrared photoplethysmography; R is an intermediate parameter in the calculation process and has no actual physical meaning. It is used to show that there is linearity between SpO2 and R.

[0118] a is approximately 104, b is approximately 17;

[0119] For the filtered photoplethysmography signal, based on the human microelastic cavity model, the blood flow velocity is approximately linearly related to the photoplethysmography period. The blood flow velocity is calculated using the following formula:

[0120]

[0121] Where BV is the blood flow velocity of the measured organism, c and d are calibration coefficients, T is the photoplethysmography period, K is the pulse waveform characteristic, which is generally taken as 1 / 3 in clinical practice, and S is the blood vessel cross-sectional area, which is taken as a constant of 500.

[0122] For the collected contact heat, radiant heat, and ambient temperature and humidity, according to the energy metabolism conservation theory, the local metabolic heat production of the body in a normal non-exercise physiological state is equal to the heat dissipation. The local metabolic rate calculation formula for the non-exercise detection site is:

[0123] BMR=W con +W eva +W rad ,

[0124] Where BMR is the local metabolic rate of the organism being measured, W con is the convection heat, W eva is the heat of vaporization, W rad It is metabolic heat;

[0125] The calculation formula for convection heat is:

[0126] W con =h×(t p -t e ),

[0127] Where h is the convective heat transfer coefficient, t pis the surface temperature of the measured organism, t e is the ambient temperature of the measured organism.

[0128] The formula for calculating the heat of vaporization is:

[0129] W eva =HK p [P p -P e ),

[0130] Where H is the heat of vaporization of water, K p is the skin permeability coefficient, P p is the saturated partial pressure of water vapor in the air at skin temperature and humidity, P e It is the saturated partial pressure of water vapor in the air at the actual ambient temperature and humidity.

[0131] The calculation formula for metabolic heat is:

[0132] W rad =εσt p 4 ,

[0133] Among them, ε is the blackness of the measured skin, and σ is the blackbody radiation constant.

[0134] The calculated blood oxygen saturation, blood flow rate, and local metabolic rate of the measured organism are input into a preset model to predict the final blood glucose concentration.

[0135] Model training method:

[0136] The blood oxygen saturation, blood flow rate, local metabolic rate, BMI index, gender, and age of the tested organism are used as RNN neural network inputs, and blood glucose concentration is used as the prediction label. The training set and the prediction set are divided into a ratio of 7:3 to train the neural network and obtain a pre-trained model.

[0137] In the description of the present invention, it should be understood that the terms "longitudinal", "transverse", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside", etc., indicating the orientation or position relationship, are based on the orientation or position relationship shown in the accompanying drawings, and are only for the convenience of describing the present invention, 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 a limitation on the present invention.

[0138] The embodiments described above are merely descriptions of preferred embodiments of the present invention and are not intended to limit the scope of the present invention. Without departing from the spirit of the present invention, various modifications and improvements made to the technical solutions of the present invention by persons skilled in the art should fall within the scope of protection defined by the claims of the present invention.

Claims

1. A patch-type non-invasive continuous blood glucose monitor, characterized in that: include: Housing (1); A signal acquisition and processing unit (3) is arranged in the housing (1), and is used to acquire biological information data and process the acquired data to predict blood glucose concentration; A power management unit (2) is arranged in the housing (1), and the power management unit (2) is used to provide energy to the signal acquisition and processing unit (3); a fixing unit (4), arranged on the housing (1), the fixing unit (4) being used to fix the housing (1) on a biological body; The biological information data collected by the signal collection and processing unit (3) at least includes the photoplethysmographic signal of the measured biological body, the contact heat of the measured biological body, the radiant heat of the measured biological body, and the temperature and humidity around the measured biological body.

2. A patch-type non-invasive continuous blood glucose monitor according to claim 1, characterized in that: The housing (1) comprises: A shell having a cavity coaxially defined therein, and an opening defined at one end of the shell, the opening being in communication with the cavity; A bottom cover (14) is arranged at the opening, and a through slot is formed on the bottom cover (14), and the through slot is communicated with the cavity; A through hole (12) is provided on the outer side wall of the housing; At least one protrusion (13) is arranged on the side wall of the cavity, and the protrusion (13) is arranged along the length direction of the shell.

3. A patch-type non-invasive continuous blood glucose monitor according to claim 2, characterized in that: The signal acquisition and processing unit (3) comprises: A circuit board is fixedly mounted in the cavity, and a groove adapted to the protrusion (13) is provided at the outer edge of the circuit board; A signal acquisition module (31) is fixedly mounted on the circuit board, the signal acquisition module (31) is arranged corresponding to the through slot, and the signal acquisition module (31) is used to collect biological information data; A signal processing module (32) is fixedly mounted on the circuit board, the signal processing module (32) is electrically connected to the signal acquisition module (31), and the signal processing module (32) is used to process the biological information data collected by the signal acquisition module (31) to predict the blood glucose concentration; A Bluetooth module (33) is fixedly mounted on the circuit board. The Bluetooth module (33) is electrically connected to the signal processing module (32). The Bluetooth module (33) is used to transmit the blood glucose concentration predicted by the signal processing module (32) to a receiving device.

4. A patch-type non-invasive continuous blood glucose monitor according to claim 3, characterized in that: The power management unit (2) comprises: A battery holder (22) is fixedly mounted on the circuit board, the battery holder (22) is electrically connected to the signal acquisition module (31), the signal processing module (32) and the Bluetooth module (33), the battery holder (22) is electrically connected to a charging cable, and a charging interface of the charging cable is arranged in the through hole 1 (12); A battery (21) is detachably connected to the battery holder (22), and the battery (21) provides energy to the signal acquisition module (31), the signal processing module (32), and the Bluetooth module (33) through the battery holder (22); A power switch (11) is provided on the housing (1), and the power switch (11) is used to disconnect or connect the connection between the battery holder (22) and the signal acquisition module (31), the signal processing module (32) and the Bluetooth module (33).

5. A patch-type non-invasive continuous blood glucose monitor according to claim 2, characterized in that: The fixing unit (4) comprises: A fixing block (41) detachably connected to the bottom cover (14); An adhesive tape (42) is provided on a side of the fixing block (41) away from the bottom cover (14), and the adhesive tape (42) is used for adhering to a biological body.

6. A blood glucose measurement method based on the patch-type non-invasive continuous blood glucose monitor according to any one of claims 1 to 5, characterized in that: The following steps are involved: Acquiring biological information data through a signal acquisition and processing unit (3), the biological information data at least including a photoplethysmographic signal of the measured biological body, contact heat of the measured biological body, radiant heat of the measured biological body, and temperature and humidity around the measured biological body; Based on a preset algorithm, the blood oxygen saturation of the measured organism is calculated based on the photoplethysmography signal of the measured organism, the blood flow velocity of the measured organism is calculated based on the photoplethysmography periodic signal of the measured organism, and the local metabolic rate of the measured organism is calculated based on the contact heat of the measured organism, the radiant heat of the measured organism, and the temperature and humidity around the measured organism; The calculated blood oxygen saturation, blood flow rate and local metabolic rate of the measured organism are input into a preset model to predict the final blood glucose concentration.

7. A blood glucose measurement method according to claim 6, characterized in that: The calculation formula of the blood oxygen saturation of the measured organism is: SpO2=(ab×R)×100%, Among them, SpO2 is the blood oxygen saturation of the measured organism, a and b are calibration coefficients, AC 550 The range of 660nm red light photoplethysmography, DC 660 is the average value of 660nm red light photoplethysmography, AC 880 The range of the photoplethysmography of the 880nm near-infrared light is DC 880 It is the average value of the 880nm near-infrared light photoplethysmography.

8. A blood glucose measurement method according to claim 6, characterized in that: The calculation formula of the blood flow rate of the measured organism is: Wherein, BV is the blood flow velocity of the measured organism, c and d are calibration coefficients, T is the photoplethysmography period, K is the pulse waveform characteristic, and S is the blood vessel cross-sectional area.

9. A blood glucose measurement method according to claim 6, characterized in that: The local metabolic rate of the measured organism is calculated as: WMD=W com +W eva +W rad , Where BMR is the local metabolic rate of the organism being measured, W com is the convection heat, W eva is the heat of vaporization, W rad It is metabolic heat.

10. A blood glucose measurement method according to claim 9, characterized in that: The calculation formula for convection heat is: W con =h×(t p -t e ), Where h is the convective heat transfer coefficient, t p is the surface temperature of the measured organism, t e is the ambient temperature of the measured organism.

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