A non-invasive blood glucose meter based on flexible biosensors

Abstract

The application discloses a non-invasive blood glucose meter based on a flexible biosensor, which comprises a flexible attaching base, a sweat sampling area, a glucose sensing electrode, a signal collecting module, a data correction module, a wireless communication module, a display terminal, a main detection micro-channel, a reference micro-channel, a reference detection electrode, a segmented liquid storage cavity, a perspiration rate detection electrode, a temperature sensor, a conductivity sensor, a pressure sensing array, a strain detection layer, an edge sealing ring and a flexible packaging film; the main detection micro-channel and the reference micro-channel are arranged, so that the sweat collected by the same sweat sampling area enters the glucose detection path and the background reference path respectively; the data correction module can differentially correct the detection signal of the glucose sensing electrode according to the background signal of the reference detection electrode, thereby reducing the influence on the detection result and improving the stability of blood glucose trend monitoring.

Description

Technical Field

[0001] This invention relates to the field of medical testing equipment technology, specifically a non-invasive blood glucose meter based on a flexible biosensor. Background Technology

[0002] Blood glucose monitoring is a crucial component of diabetes management and metabolic health assessment. Current blood glucose testing methods primarily include finger-prick blood sampling and continuous glucose monitoring (CGM). Finger-prick blood sampling requires pricking the skin to obtain a blood sample, which can lead to pain, infection risks, and decreased adherence with long-term use. While CGM allows for longer data recording periods, its sensor probes typically need to penetrate subcutaneous tissue, making it still an invasive method. This presents challenges such as foreign body sensation, local irritation, and high replacement costs.

[0003] With the development of flexible electronics, biosensors, and wearable devices, non-invasive blood glucose monitoring using sweat and other bodily secretions has gradually gained attention. Flexible biosensors can adhere to the surface of human skin and have advantages such as being thin, flexible, and comfortable to wear. They can be used to collect glucose-related signals from sweat. However, in practical use, existing sweat-based non-invasive blood glucose testing devices suffer from several problems. The glucose concentration in sweat is low and easily affected by sweat salt, sebum residue, temperature changes, and other non-glucose components, leading to signal drift in the sensor electrode output. On the other hand, the rate of sweat production is greatly affected by exercise, ambient temperature, and individual differences. When the sweat flow rate is too fast, it will dilute the test sample; when the sweat flow rate is too slow, local evaporation and concentration are likely to occur, affecting the stability of the test results. Therefore, it is necessary to design a flexible biosensor non-invasive blood glucose meter that can perform sweat reference calibration, sampling state compensation, and adhesion state recognition to improve the reliability of non-invasive blood glucose trend monitoring. Summary of the Invention

[0004] The purpose of this invention is to provide a non-invasive blood glucose meter based on a flexible biosensor, in order to solve the problems mentioned in the background art of existing sweat-based non-invasive blood glucose detection devices, which are easily affected by changes in sweat background components, sweating rate, and unstable adhesion, resulting in signal drift and inaccurate blood glucose trend judgment.

[0005] To achieve the above objectives, the present invention provides the following technical solution: a non-invasive blood glucose meter based on a flexible biosensor, comprising a flexible adhesive substrate, a sweat sampling area, a glucose sensing electrode, a signal acquisition module, a data correction module, a wireless communication module, and a display terminal, and further comprising a main detection microchannel, a reference microchannel, a reference detection electrode, a segmented reservoir, a sweat rate detection electrode, a temperature sensor, a conductivity sensor, a pressure sensing array, a strain detection layer, an edge sealing ring, and a flexible encapsulation film; the sweat sampling area is disposed on the side of the flexible adhesive substrate close to the skin, and the segmented reservoir is connected to the sweat sampling area. The main detection microchannel and the reference microchannel are both connected to the segmented liquid storage chamber; the glucose sensing electrode is located in the main detection microchannel, and the reference detection electrode is located in the reference microchannel; the pressure sensing array is located on the side of the flexible adhesive substrate closest to the skin, and the strain detection layer is located in the flexible adhesive substrate; the glucose sensing electrode, the reference detection electrode, the sweat rate detection electrode, the temperature sensor, the conductivity sensor, the pressure sensing array, and the strain detection layer are all electrically connected to the signal acquisition module, the signal acquisition module is electrically connected to the data correction module, and the data correction module communicates with the display terminal through the wireless communication module.

[0006] In this preferred embodiment of the technical solution, the inlets of the main detection microchannel and the reference microchannel are both connected to the same sweat sampling area, so that the main detection microchannel and the reference microchannel receive sweat samples from the same skin region.

[0007] Based on the preferred embodiment of this technical solution, the segmented liquid storage chamber includes multiple liquid storage units arranged sequentially along the direction of sweat flow, and the sweat rate detection electrode is disposed between adjacent liquid storage units to detect the time interval between sweat entering each liquid storage unit.

[0008] Based on the preferred embodiment of this technical solution, the surface of the glucose sensing electrode is provided with a glucose-responsive film layer, the surface of the reference detection electrode is provided with a non-glucose-responsive reference film layer, and the data correction module performs differential correction on the main detection signal output by the glucose sensing electrode according to the background signal output by the reference detection electrode.

[0009] In this preferred embodiment of the technical solution, the temperature sensor is positioned near the main detection microchannel, and the conductivity sensor is positioned near the reference microchannel. The data correction module performs temperature compensation and conductivity compensation on the sweat glucose signal based on the detection signals from the temperature sensor and the conductivity sensor.

[0010] Based on the preferred embodiment of this technical solution, the pressure sensing array includes multiple flexible pressure sensing units spaced apart. These multiple flexible pressure sensing units are distributed around the sweat sampling area to detect the contact pressure distribution between the flexible adhesive substrate and the skin.

[0011] According to the preferred embodiment of this technical solution, the strain detection layer includes a first strain detection part extending along the length direction of the flexible adhesive substrate and a second strain detection part extending along the width direction of the flexible adhesive substrate, which is used to detect the tensile deformation and bending deformation generated by the flexible adhesive substrate in the wearing state.

[0012] Based on the preferred embodiment of this technical solution, an edge sealing ring is arranged around the sweat sampling area, the main detection microchannel, the reference microchannel, and the segmented liquid storage chamber, and a flexible encapsulation film is covered above the main detection microchannel, the reference microchannel, and the segmented liquid storage chamber to limit the flow path of sweat within the flexible adhesive substrate.

[0013] Based on the preferred embodiment of this technical solution, a non-invasive blood glucose trend monitoring method using a non-invasive blood glucose meter based on a flexible biosensor, as described above, includes the following steps: S1. Collect sweat from the skin surface through the sweat sampling area and allow the sweat to enter the segmented liquid storage chambers in sequence; S2. The time it takes for sweat to enter the segmented storage chamber is detected by the sweat rate detection electrode to obtain the sweat rate signal; S3. Allow sweat to enter the main detection microchannel and the reference microchannel respectively. Obtain the main detection signal through the glucose sensing electrode and the background signal through the reference detection electrode. S4. Collect temperature and conductivity signals of the sweat detection area using temperature and conductivity sensors; S5. Acquire the attachment status signal of the flexible substrate through the pressure sensing array and strain detection layer; S6. The main detection signal is subjected to reference subtraction, temperature compensation, conductivity compensation, sweating rate compensation and adhesion state compensation through the data correction module to obtain the blood glucose trend value. S7. The blood glucose trend value is sent to the display terminal via the wireless communication module.

[0014] In step S6, the data correction module generates an adhesion status value based on the contact pressure distribution detected by the pressure sensing array and the patch deformation degree detected by the strain detection layer. When the adhesion status value is lower than the preset acceptance threshold, the data correction module marks the main detection signal of the corresponding time period as contact abnormal data and stops directly including the main detection signal of that time period in the calculation of blood glucose trend value.

[0015] Compared with the prior art, the beneficial effects of the present invention are: 1. This invention sets up a main detection microchannel and a reference microchannel, so that sweat collected from the same sweat sampling area enters the glucose detection path and the background reference path respectively. The data correction module can perform differential correction on the detection signal of the glucose sensing electrode according to the background signal of the reference detection electrode, thereby reducing the influence of sweat salt, skin residue and non-glucose components on the detection results and improving the stability of blood glucose trend monitoring.

[0016] 2. This invention, by setting up segmented liquid storage chambers and sweat rate detection electrodes, can record the sequence of sweat entering different liquid storage areas and the filling time, enabling the device to obtain information on sweat sampling time and sweat rate. The data correction module then compensates for dilution deviations caused by excessively fast sweat flow and concentration deviations caused by excessively slow flow, avoiding the direct judgment of blood glucose trends based solely on sweat glucose concentration.

[0017] 3. This invention, by setting a pressure sensing array and a strain detection layer on a flexible adhesive substrate, can simultaneously detect the contact pressure distribution between the patch and the skin, as well as the bending deformation state during wear. When the patch exhibits edge lifting, insufficient local compression, or excessive deformation, the data correction module can mark the corresponding time period data as abnormal data, reducing misjudgments caused by movement and unstable wear, and making the blood glucose trend curve output by the display terminal more stable and reliable. Attached Figure Description

[0018] Figure 1 This is a schematic diagram of one embodiment of a non-invasive blood glucose meter based on a flexible biosensor according to the present invention; Figure 2 This is a schematic diagram illustrating the operational state of the present invention when it is in contact with human skin; Figure 3 This is a perspective view of the distribution structure of each module in this invention; Figure 4 This is a schematic diagram of the overall exploded structure of the present invention; Figure 5 This is a schematic diagram of the principle framework of the present invention.

[0019] In the diagram: 1. Flexible adhesive substrate; 2. Sweat sampling area; 3. Main detection microchannel; 4. Reference microchannel; 5. Glucose sensing electrode; 6. Reference detection electrode; 7. Segmented reservoir; 8. Sweat rate detection electrode; 9. Temperature sensor; 10. Conductivity sensor; 11. Pressure sensing array; 12. Strain detection layer; 13. Edge sealing ring; 14. Flexible encapsulation film; 15. Signal acquisition module; 16. Data correction module; 17. Wireless communication module; 18. Display terminal. Detailed Implementation

[0020] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0021] Please see Figure 1-5 This invention provides an embodiment of a non-invasive blood glucose meter based on a flexible biosensor, comprising a flexible adhesive substrate 1, a sweat sampling area 2, a glucose sensing electrode 5, a signal acquisition module 15, a data correction module 16, a wireless communication module 17, and a display terminal 18. It also includes a main detection microchannel 3, a reference microchannel 4, a reference detection electrode 6, a segmented reservoir 7, a sweat rate detection electrode 8, a temperature sensor 9, a conductivity sensor 10, a pressure sensing array 11, a strain detection layer 12, an edge sealing ring 13, and a flexible encapsulation film 14. The sweat sampling area 2 is disposed on the side of the flexible adhesive substrate 1 closest to the skin. The segmented reservoir 7 is connected to the sweat sampling area 2. Both the main detection microchannel 3 and the reference microchannel 4 are connected to the segmented reservoir 7. The glucose sensing electrode 5 is disposed within the main detection microchannel 3, and the reference detection electrode 6 is disposed within the reference microchannel 4. The force sensing array 11 is disposed on the side of the flexible adhesive substrate 1 closest to the skin, and the strain detection layer 12 is disposed within the flexible adhesive substrate 1. The glucose sensing electrode 5, the reference detection electrode 6, the sweat rate detection electrode 8, the temperature sensor 9, the conductivity sensor 10, the pressure sensing array 11, and the strain detection layer 12 are all electrically connected to the signal acquisition module 15. The signal acquisition module 15 is electrically connected to the data correction module 16. The data correction module 16 is connected to the display terminal 18 via the wireless communication module 17. Through the cooperation of the flexible adhesive substrate 1, the sweat sampling area 2, the main detection microchannel 3, the reference microchannel 4, the pressure sensing array 11, and the data correction module 16, the present invention can simultaneously complete sweat collection, glucose detection, background reference, and adhesion status judgment, avoiding errors caused by direct output of a single detection signal and improving the overall reliability of non-invasive blood glucose trend monitoring.

[0022] Please see Figure 3 A further solution based on this embodiment is as follows: the inlets of the main detection microchannel 3 and the reference microchannel 4 are both connected to the same sweat sampling area 2, so that the main detection microchannel 3 and the reference microchannel 4 receive sweat samples from the same skin area. Since the main detection microchannel 3 and the reference microchannel 4 are both connected to the same sweat sampling area 2, it can ensure that the sweat in the two channels comes from the same skin area and the same sampling time period, so that the background signal collected by the reference detection electrode 6 is closer to the interference received by the glucose sensing electrode 5, which is convenient for subsequent differential correction.

[0023] Please see Figure 3 and Figure 4 A further solution based on this embodiment is as follows: the segmented liquid storage chamber 7 includes multiple liquid storage units arranged sequentially along the direction of sweat flow, and the sweat rate detection electrode 8 is disposed between adjacent liquid storage units to detect the time interval of sweat entering each liquid storage unit. The segmented liquid storage chamber 7 is arranged sequentially along the direction of sweat flow and works in conjunction with the sweat rate detection electrode 8 to detect the time of sweat entering each liquid storage unit, which is beneficial for determining the order of sweat sampling and sweat rate, and reducing the impact of excessively rapid dilution and excessively slow concentration of sweat on the detection results.

[0024] Please see Figure 3 and Figure 4 A further solution based on this embodiment is as follows: a glucose-responsive film layer is provided on the surface of the glucose sensing electrode 5, and a non-glucose-responsive reference film layer is provided on the surface of the reference detection electrode 6. The data correction module 16 performs differential correction on the main detection signal output by the glucose sensing electrode 5 according to the background signal output by the reference detection electrode 6. The glucose sensing electrode 5 is used to acquire the main detection signal, and the reference detection electrode 6 is used to acquire the sweat background signal. The data correction module 16 performs differential correction on the two types of signals, which can reduce the baseline drift caused by sweat salt, skin residue and non-glucose components.

[0025] Please see Figure 3 and Figure 4 A further solution based on this embodiment is as follows: the temperature sensor 9 is located near the main detection microchannel 3, and the conductivity sensor 10 is located near the reference microchannel 4. The data correction module 16 performs temperature compensation and conductivity compensation on the sweat glucose signal based on the detection signals of the temperature sensor 9 and the conductivity sensor 10. The temperature sensor 9 and the conductivity sensor 10 respectively collect the temperature signal and conductivity signal of the detection area, so that the data correction module 16 can perform environmental state compensation on the sweat glucose signal, reducing the detection deviation caused by temperature changes and changes in sweat salt concentration.

[0026] Please see Figure 3 and Figure 4 A further solution based on this embodiment is as follows: the pressure sensing array 11 includes multiple flexible pressure sensing units arranged at intervals. The multiple flexible pressure sensing units are distributed around the sweat sampling area 2 and are used to detect the contact pressure distribution between the flexible adhesive base 1 and the skin. The pressure sensing array 11 is composed of multiple flexible pressure sensing units and is distributed around the sweat sampling area 2. It can determine the contact pressure distribution between the flexible adhesive base 1 and the skin in real time, which is convenient for identifying abnormal wearing conditions such as patch lifting, local loosening and insufficient compression.

[0027] Please see Figure 3 and Figure 4A further solution based on this embodiment is as follows: the strain detection layer 12 includes a first strain detection part extending along the length direction of the flexible adhesive substrate 1 and a second strain detection part extending along the width direction of the flexible adhesive substrate 1, which are used to detect the tensile deformation and bending deformation generated by the flexible adhesive substrate 1 in the wearing state. The strain detection layer 12 is provided with the first strain detection part and the second strain detection part, which can detect the deformation of the flexible adhesive substrate 1 in the length direction and the width direction respectively, so that the device can identify the stretching, bending and twisting state during the wearing process and reduce the influence of motion deformation on the detection data.

[0028] Please see Figure 3 and Figure 4 A further solution based on this embodiment is as follows: an edge sealing ring 13 is provided around the sweat sampling area 2, the main detection microchannel 3, the reference microchannel 4, and the segmented liquid storage cavity 7. A flexible encapsulation film 14 is covered above the main detection microchannel 3, the reference microchannel 4, and the segmented liquid storage cavity 7 to limit the flow path of sweat in the flexible adhesive substrate 1. The edge sealing ring 13 is provided around the sweat sampling area 2, the main detection microchannel 3, the reference microchannel 4, and the segmented liquid storage cavity 7. The flexible encapsulation film 14 covers the top of each channel, which can limit the flow path of sweat and reduce the entry of external moisture, dust, and skin surface impurities into the detection area.

[0029] Please see Figure 5 A further solution based on this embodiment is: a non-invasive blood glucose trend monitoring method using the above-mentioned non-invasive blood glucose meter based on a flexible biosensor, comprising the following steps: S1. Collect sweat from the skin surface through the sweat sampling area 2, and allow the sweat to enter the segmented liquid storage chamber 7 in sequence; S2. The time it takes for sweat to enter the segmented storage chamber 7 is detected by the sweat rate detection electrode 8 to obtain the sweat rate signal; S3. Sweat is introduced into the main detection microchannel 3 and the reference microchannel 4 respectively. The main detection signal is obtained through the glucose sensing electrode 5, and the background signal is obtained through the reference detection electrode 6. S4. The temperature signal and conductivity signal of the sweat detection area are collected by the temperature sensor 9 and the conductivity sensor 10. S5. The attachment status signal of the flexible attachment substrate 1 is acquired through the pressure sensing array 11 and the strain detection layer 12. S6. The main detection signal is subjected to reference subtraction, temperature compensation, conductivity compensation, sweating rate compensation and adhesion state compensation through the data correction module 16 to obtain the blood glucose trend value. S7. The blood glucose trend value is sent to the display terminal 18 via the wireless communication module 17.

[0030] Please see Figure 5A further solution based on this embodiment is as follows: In step S6, the data correction module 16 generates an adhesion status value based on the contact pressure distribution detected by the pressure sensing array 11 and the patch deformation degree detected by the strain detection layer 12. When the adhesion status value is lower than the preset acceptance threshold, the data correction module 16 marks the main detection signal of the corresponding time period as contact abnormal data and stops directly including the main detection signal of that time period in the calculation of blood glucose trend value. In step S6, the data correction module 16 generates an adhesion status value based on the signals of the pressure sensing array 11 and the strain detection layer 12, and marks the data that is lower than the preset acceptance threshold as abnormal. This can prevent the main detection signal when the contact is poor from directly participating in the calculation and improve the reliability of blood glucose trend judgment.

[0031] Working principle: In use, the flexible adhesive substrate 1 is attached to the surface of human skin, and the edge sealing ring 13 is pressed tightly against the periphery of the flexible adhesive substrate 1, so that the sweat sampling area 2 forms a sampling space relatively isolated from the external environment. The flexible encapsulation film 14 covers the main detection microchannel 3, the reference microchannel 4, and the segmented liquid storage chamber 7 to restrict the sweat flow path and prevent sweat from seeping into the detection area from the edge of the patch, thereby reducing the influence of external moisture, sebum, and dust on the detection signal. The sweat generated on the surface of human skin first enters the sweat sampling area 2. The inner surface of the sweat sampling area 2 is provided with a hydrophilic guiding layer, so that the sweat can be introduced into the segmented liquid storage chamber 7 by capillary action. The segmented liquid storage chambers 7 are arranged sequentially along the direction of sweat flow. The order in which the sweat enters the different segmented liquid storage chambers 7 represents different sampling time periods and sweating rates. The detection electrode 8 is located near the segmented liquid storage chamber 7. When sweat fills each segmented liquid storage chamber 7 in sequence, the conduction signal of the sweat rate detection electrode 8 changes. The signal acquisition module 15 obtains the sweat filling time and sweat rate accordingly. The sweat passing through the segmented liquid storage chamber 7 is then distributed to the main detection microchannel 3 and the reference microchannel 4. The inlets of the main detection microchannel 3 and the reference microchannel 4 are both connected to the same sweat sampling area 2, so that the two microchannels obtain sweat samples from the same skin area and the same sampling time period. A glucose sensing electrode 5 is set in the main detection microchannel 3. A glucose response membrane layer is provided on the surface of the glucose sensing electrode 5. When glucose in the sweat comes into contact with the glucose response membrane layer, an electrochemical response is generated. The signal acquisition module 15 collects the electrochemical response and converts it into a main glucose detection signal.

[0032] A reference detection electrode 6 is disposed within the reference microfluidic channel 4. The reference detection electrode 6 does not have a glucose-responsive membrane layer; instead, it is used to acquire the sweat background signal. This background signal includes the sweat background electrochemical signal, conductivity changes caused by salt, and baseline drift caused by non-glucose components. A conductivity sensor 10 detects the conductivity state of the sweat, and a temperature sensor 9 detects the temperature of the skin surface and the area where the sweat is located. A signal acquisition module 15 simultaneously acquires signals from the glucose sensing electrode 5, the reference detection electrode 6, the sweat rate detection electrode 8, the temperature sensor 9, and the conductivity sensor 10, and sends these signals to a digital sensor. According to the correction module 16, during the data processing, the data correction module 16 first reads the main glucose detection signal output by the main detection microchannel 3, and then reads the background signal output by the reference microchannel 4. Since the main detection microchannel 3 and the reference microchannel 4 have the same source of sweat, the background signal generated by the reference detection electrode 6 can reflect the common interference caused by sweat salt content, skin surface residue and changes in ambient temperature. Based on the background signal of the reference detection electrode 6, the data correction module 16 performs differential subtraction on the main glucose detection signal of the glucose sensing electrode 5 to obtain the preliminarily corrected sweat glucose signal.

[0033] Subsequently, the data correction module 16 combines the signal from the sweat rate detection electrode 8 to perform sampling state compensation on the sweat glucose signal. When the sweat rate is fast, the residence time of sweat in the sweat sampling area 2, segmented reservoir 7, main detection microchannel 3, and reference microchannel 4 is shortened, and the data correction module 16 increases the flow rate compensation weight of the signal during this period. When the sweat rate is slow, the residence time of sweat in the microchannel is extended, and the data correction module 16 reduces the deviation signal caused by local evaporation and concentration. Through this processing, the device can avoid directly outputting results based solely on sweat glucose concentration, making the output data more suitable for reflecting blood glucose change trends. At the same time, the pressure sensing array 11 is disposed on the side of the flexible adhesive substrate 1 closest to the skin, and the strain detection layer 12 is disposed within the flexible adhesive substrate 1. The pressure sensing array 11 is used to detect the contact between the flexible adhesive substrate 1 and the skin. Pressure distribution and strain detection layer 12 are used to detect the degree of deformation of the patch when the arm is bent, the skin is stretched, and the body moves. Signal acquisition module 15 sends the signals from pressure sensing array 11 and strain detection layer 12 to data correction module 16. Data correction module 16 generates attachment status value accordingly. When pressure sensing array 11 detects that the local pressure is too low and strain detection layer 12 detects that the patch deformation is too large, data correction module 16 determines that the flexible attachment substrate 1 has an unstable adhesion state. At this time, data correction module 16 does not directly output the main glucose detection signal of this period as effective blood glucose trend data, but marks the data of this period as contact abnormal data. When pressure sensing array 11 detects that the pressure distribution is stable and strain detection layer 12 detects that the patch deformation is within the allowable range, data correction module 16 includes the data of this period in blood glucose trend calculation.

[0034] Under effective sampling conditions, the data correction module 16 sequentially completes reference deduction, temperature compensation, conductivity compensation, sweating rate compensation, and adhesion state compensation. The compensated data does not use a single sweat glucose concentration as the final result, but instead forms a blood glucose trend value. This blood glucose trend value is used to reflect the state of blood glucose rise, fall, and stable change, which can reduce misjudgments caused by fluctuations in sweat composition, unstable patch contact, and motion interference.

[0035] The wireless communication module 17 is connected to the data correction module 16 and is used to send the blood glucose trend value, the attachment status value, the sweating rate information and the abnormal data marker to the display terminal 18. After receiving the data, the display terminal 18 displays a continuous blood glucose trend curve and issues a prompt when the patch contact is unstable, the sweat sampling is insufficient, the sweat flow rate is abnormal, or the signal drift increases, so that the user can adjust the wearing position and attachment pressure of the flexible attachment base 1 in time.

[0036] Although embodiments of the invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the invention, the scope of which is defined by the appended claims and their equivalents.

Claims

1. A non-invasive blood glucose meter based on a flexible biosensor, comprising a flexible attachment substrate (1), a sweat sampling area (2), a glucose sensing electrode (5), a signal acquisition module (15), a data correction module (16), a wireless communication module (17), and a display terminal (18), characterized in that: It also includes a main detection microfluidic channel (3), a reference microfluidic channel (4), a reference detection electrode (6), a segmented liquid storage chamber (7), a sweat rate detection electrode (8), a temperature sensor (9), a conductivity sensor (10), a pressure sensing array (11), a strain detection layer (12), an edge sealing ring (13), and a flexible encapsulation film (14); the sweat sampling area (2) is located on the side of the flexible adhesive substrate (1) close to the skin, the segmented liquid storage chamber (7) is connected to the sweat sampling area (2), and both the main detection microfluidic channel (3) and the reference microfluidic channel (4) are connected to the segmented liquid storage chamber (7); the glucose sensing electrode (5) is located in the main detection microfluidic channel (3), the reference detection electrode (6), and the reference detection electrode (7) is located in the segmented liquid storage chamber (8). Electrode (6) is disposed in reference microchannel (4); pressure sensing array (11) is disposed on the side of flexible adhesive substrate (1) close to the skin; strain detection layer (12) is disposed in flexible adhesive substrate (1); glucose sensing electrode (5), reference detection electrode (6), sweating rate detection electrode (8), temperature sensor (9), conductivity sensor (10), pressure sensing array (11) and strain detection layer (12) are all electrically connected to signal acquisition module (15), signal acquisition module (15) is electrically connected to data correction module (16), and data correction module (16) is connected to display terminal (18) through wireless communication module (17).

2. The non-invasive blood glucose meter based on a flexible biosensor according to claim 1, characterized in that: The inlets of the main detection microchannel (3) and the reference microchannel (4) are both connected to the same sweat sampling area (2), so that the main detection microchannel (3) and the reference microchannel (4) receive sweat samples from the same skin area.

3. A non-invasive blood glucose meter based on a flexible biosensor according to claim 1, characterized in that: The segmented liquid storage chamber (7) includes multiple liquid storage units arranged sequentially along the direction of sweat flow. The sweat rate detection electrode (8) is set between adjacent liquid storage units to detect the time interval between sweat entering each liquid storage unit.

4. A non-invasive blood glucose meter based on a flexible biosensor according to claim 1, characterized in that: The glucose sensing electrode (5) has a glucose-responsive film layer on its surface, and the reference detection electrode (6) has a non-glucose-responsive reference film layer on its surface. The data correction module (16) performs differential correction on the main detection signal output by the glucose sensing electrode (5) based on the background signal output by the reference detection electrode (6).

5. A non-invasive blood glucose meter based on a flexible biosensor according to claim 1, characterized in that: The temperature sensor (9) is located near the main detection microchannel (3), and the conductivity sensor (10) is located near the reference microchannel (4). The data correction module (16) performs temperature compensation and conductivity compensation on the sweat glucose signal based on the detection signals of the temperature sensor (9) and the conductivity sensor (10).

6. A non-invasive blood glucose meter based on a flexible biosensor according to claim 1, characterized in that: The pressure sensing array (11) includes multiple flexible pressure sensing units spaced apart and distributed around the sweat sampling area (2) to detect the contact pressure distribution between the flexible adhesive substrate (1) and the skin.

7. A non-invasive blood glucose meter based on a flexible biosensor according to claim 1, characterized in that: The strain detection layer (12) includes a first strain detection part extending along the length direction of the flexible adhesive substrate (1) and a second strain detection part extending along the width direction of the flexible adhesive substrate (1), which is used to detect the tensile deformation and bending deformation generated by the flexible adhesive substrate (1) in the wearing state.

8. A non-invasive blood glucose meter based on a flexible biosensor according to claim 1, characterized in that: An edge sealing ring (13) is provided around the sweat sampling area (2), the main detection microchannel (3), the reference microchannel (4) and the segmented liquid storage chamber (7), and a flexible encapsulation film (14) is provided above the main detection microchannel (3), the reference microchannel (4) and the segmented liquid storage chamber (7) to limit the flow path of sweat in the flexible adhesive substrate (1).

9. A method for non-invasive blood glucose trend monitoring using a non-invasive blood glucose meter based on a flexible biosensor as described in any one of claims 1 to 8, characterized in that, Includes the following steps: S1. Collect sweat from the skin surface through the sweat sampling area (2) and allow the sweat to enter the segmented storage chamber (7) in sequence. S2. The time it takes for sweat to enter the segmented storage chamber (7) is detected by the sweat rate detection electrode (8) to obtain the sweat rate signal; S3. Sweat enters the main detection microchannel (3) and the reference microchannel (4) respectively. The main detection signal is obtained through the glucose sensing electrode (5), and the background signal is obtained through the reference detection electrode (6). S4. The temperature signal and conductivity signal of the sweat detection area are collected by the temperature sensor (9) and the conductivity sensor (10); S5. The attachment status signal of the flexible attachment substrate (1) is collected through the pressure sensing array (11) and the strain detection layer (12); S6. The main detection signal is subjected to reference subtraction, temperature compensation, conductivity compensation, sweating rate compensation and adhesion state compensation through the data correction module (16) to obtain the blood glucose trend value. S7. The blood glucose trend value is sent to the display terminal (18) via the wireless communication module (17).

10. The non-invasive blood glucose trend monitoring method according to claim 9, characterized in that: In step S6, the data correction module (16) generates an attachment status value based on the contact pressure distribution detected by the pressure sensing array (11) and the patch deformation degree detected by the strain detection layer (12). When the attachment status value is lower than the preset acceptance threshold, the data correction module (16) marks the main detection signal of the corresponding time period as contact abnormal data and stops directly including the main detection signal of that time period into the blood glucose trend value calculation.

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