A method for detecting glucose in sweat based on an organic electrochemical transistor sensor

Abstract

This invention discloses a method for detecting glucose in sweat based on an organic electrochemical transistor (OECT) sensor, comprising the following steps: 1. Preparation of materials such as H-rGO-Pt NPs; 2. Electrode modification and construction of a biosensor interface; 3. Plotting a working curve for glucose in sweat; 4. Detection of glucose in multiple artificial sweat samples. This method fully utilizes the properties of gold nanoparticles that enhance electron transport, the effective current signal amplification and excellent load capacity of the OECT sensor, and combines it with high-affinity glucose oxidase to successfully prepare a glucose oxidase sensor based on Au-PB-PEDOT nanocomposite materials. This provides a new method for detecting glucose in sweat, offering high detection efficiency and sensitivity.

Description

Technical Field

[0001] This invention relates to the field of electrochemical detection technology, specifically to a method for detecting glucose in sweat based on an organic electrochemical transistor sensor. Background Technology

[0002] Clinically, blood glucose monitoring methods include capillary blood glucose monitoring (SMBG) and continuous glucose monitoring (CMG) for multiple days. Currently, the most common blood glucose meters on the market primarily monitor changes in blood glucose levels by indirectly monitoring glucose concentrations in bodily fluids such as saliva, urine, tears, sweat, and tissue fluid. Methods for detecting sweat glucose levels include: sweat glucose detection devices based on flexible substrate electrode arrays; detection using antibacterial socks; visual detection methods based on flexible polymer gel films; vehicle-mounted sweat glucose detection systems; sweat glucose detection using flexible electrochemical transistors based on glycerol gel; detection using wearable fabric-based electrochemical sweat sensors; detection using wearable sweat sensors based on unidirectional flow-guiding fabrics; and detection using novel transdermal systems. For example, patent CN112394100A discloses a method for constructing a source, drain, and gate electrode using a flexible PET substrate. A single layer of graphene is transferred between the source and drain electrodes via a wet transfer process to form a channel. The gate electrode is functionalized by co-depositing a nanocomposite of gold and graphene. This patent provides an enzyme-free and non-invasive method for detecting glucose in bodily fluids using glycerol gel as an electrolyte. However, this method requires sufficient electrolyte solution for detection and cannot be portable or wearable. Patent CN115290729A discloses a method involving a power supply, four sweat glucose detection devices, a flexible temperature sensor, and a microcontroller arranged between a flexible substrate and flexible packaging. This method achieves autonomous power generation and real-time monitoring of sweat glucose levels during detection. However, this method is highly susceptible to external factors and cannot provide real-time monitoring, rendering it impractical. These methods are complex, time-consuming, and technically demanding, highlighting the urgent need for a rapid, sensitive, and easy-to-operate method for detecting glucose in sweat. Summary of the Invention

[0003] The purpose of this invention is to provide a method for detecting glucose in sweat based on an organic electrochemical transistor (OECT) sensor, so as to improve the detection efficiency and sensitivity of glucose in sweat.

[0004] To achieve the above objectives, the technical solution adopted by the present invention is as follows:

[0005] A method for detecting glucose in sweat based on an organic electrochemical transistor sensor includes the following steps:

[0006] Step 1: Material Preparation

[0007] (1) Preparation of chloroauric acid solution: Chloroauric acid powder is added to a brown glass bottle containing sulfuric acid and stirred until it is dissolved evenly. The chloroauric acid solution is measured and diluted with deionized water to obtain HAuCl4 solution; preferably, the sulfuric acid is prepared by diluting concentrated sulfuric acid with a mass fraction of 95%-98%.

[0008] (2) Preparation of Prussian blue solution: Hydrochloric acid, potassium chloride, ferric chloride and potassium ferricyanide were mixed to prepare PB solution.

[0009] (3) Preparation of poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate: Measure out poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate and mix it evenly with acetonitrile. Place it under a constant temperature magnetic stirrer and stir overnight to obtain PEDOT:PSS.

[0010] Step 2: Electrode modification and construction of biosensing interface

[0011] (1) Preparation of Au / SPE: The unactivated electrode was placed in a dilute sulfuric acid solution and cyclic voltammetry was performed to obtain the activated electrode SPE. The activated electrode was immersed in HAuCl4 solution and stirred under a magnetic stirrer for constant potential deposition. Then it was rinsed with pure water and dried to obtain the Au / SPE electrode. Preferably, the concentration of the dilute sulfuric acid solution was 0.5 mol / L.

[0012] (2) Preparation of PB-Au / SPE sensing interface: Glutaraldehyde solution was placed in Au / SPE electrode, rinsed with PBS solution and pure water, and dried; PB solution was added dropwise, constant potential deposition was performed, rinsed with PBS solution and pure water, and dried to obtain PB-Au / SPE sensing interface; preferably, the mass fraction of glutaraldehyde was 2.5%.

[0013] (3) Construction of PEDOT-PB-Au / SPE electrochemical sensor: The prepared PB-Au / SPE sensing interface was placed in a poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate solution and stirred under a magnetic stirrer for constant potential deposition. Then, it was rinsed with pure water and dried to obtain the PEDOT-PB-Au / SPE sensing interface. Glucose oxidase solution was dropped onto the PEDOT-PB-Au / SPE sensing interface and placed in a shaking incubator for incubation. After rinsing with water and drying, the GOx-PEDOT-PB-Au / SPE electrochemical sensor was obtained. Preferably, the glucose oxidase concentration was 0.5 g / mL.

[0014] Step 3: Plotting the working curve of sweat glucose

[0015] (1) Add the standard artificial sweat solution to the GOx-PEDOT-PB-Au / SPE electrochemical sensor obtained in step 2, incubate, wash with PBS solution to obtain the working electrode, and air dry for later use.

[0016] (2) Place the working electrode in PBS solution and use CV scanning on an electrochemical workstation to record its peak current.

[0017] (3) Test the glucose in sweat at different concentrations and plot the standard curve.

[0018] Step 4: Detection of glucose in multiple artificial sweat samples

[0019] (1) In the GOx-PEDOT-PB-Au / SPE electrochemical sensor obtained in step 2, add the same concentration of artificial sweat sample without additive, the same concentration of artificial sweat sample with added lactic acid, and the same concentration of artificial sweat sample with added uric acid respectively, incubate, wash with PBS solution to obtain 3 sets of working electrodes, and air dry for later use.

[0020] (2) Place the working electrode in PBS solution, perform CV scan, and record its peak current.

[0021] (3) The concentration of glucose in the artificial sweat to be tested is calculated based on the standard curve described in step 3.

[0022] The detection principle of this invention is as follows: Au-PB-PEDOT is modified onto the surface of a screen-printed electrode using electrodeposition technology and electrostatic adsorption. Glucose oxidase (GOD) is loaded onto the Au-PB-PEDOT material surface through non-covalent bonding and intermolecular forces. Glucose oxidase GOD exhibits strong specificity for β-D-glucose, specifically catalyzing the conversion of β-D-glucose to gluconic acid and hydrogen peroxide under aerobic conditions. GOD is a homodimeric molecule containing two flavin adenine dinucleotide (FAD) binding sites. Each monomer contains two completely different regions: one non-covalently but tightly bound to a portion of the FAD, primarily a β-sheet; the other bound to the substrate β-D-glucose, consisting of four α-helices supporting one antiparallel β-sheet, thus enabling modification onto the electrode. After adding GOD to the biosensor interface, glucose in sweat specifically binds to GOD, forming a glucose oxidase complex with a stable spatial structure, thereby arranging it orderly on the electrode surface. Au nanoparticles, due to their unique optical properties, surface plasmon absorption and resonance effects, good stability, and biocompatibility, are widely used in biomedicine, surface-enhanced Raman scattering, catalysis, and heavy metal ion detection. Au and Prussian blue (PB), as excellent conductive media, can be adsorbed onto electrode surfaces to generate electrochemical signals. The highly conductive polymer PEDOT provides high conductivity for screen-printed three-electrode systems, amplifying the detection signal in organic electrochemical transistor (OECT) sensors and thus improving sensor sensitivity. This invention uses glucose oxidase (GOD) as a recognition probe. Based on the excellent electron transfer effect and superior loading capacity of the gold nanoparticle-Prussian blue-highly conductive polymer (Au-PB-PEDOT-GOx) composite material, glucose oxidase can specifically recognize and bind to glucose in sweat. This invention constructs a sensor detection method for specifically recognizing and quantitatively analyzing glucose in sweat, achieving high detection efficiency.

[0023] In the preferred embodiment of the above scheme, the preparation process of the chloroauric acid solution in step 1 is as follows: Weigh 0.157532 mg of chloroauric acid powder with a plastic spatula, add it to a brown glass bottle containing 200 ml of 2 mM sulfuric acid, stir with a glass rod to dissolve it evenly, measure 2 ml of 5.7 mM chloroauric acid solution and add 3 ml of deionized water to dilute and prepare a 5 mM / L HAuCl4 solution.

[0024] Preferably, the Prussian blue solution in step 1 is prepared by using 0.01M hydrochloric acid, 0.1M potassium chloride, 5mM ferric chloride, and 5mM potassium ferricyanide to prepare the Prussian blue solution.

[0025] Preferably, the preparation process of poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate in step 1 is as follows: 5 μL of poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate is measured and mixed evenly with 5 mL of acetonitrile, and then stirred under a constant temperature magnetic stirrer overnight to obtain a PEDOT:PSS solution.

[0026] Preferably, in step 2, the working electrode is placed in 0.5 mol / L H2SO4 for 20 cyclic voltammetric scans, with a voltage range of -0.2V to 1.0V.

[0027] Preferably, in step 2(1), the HAuCl4 used has a mass fraction of 0.01%, a concentration of 1 mg / mL, a deposition potential of 0.4 V, and a deposition time of 120 s.

[0028] Preferably, in steps 3 and 4, the incubation temperature of the working electrode is 25°C and the incubation time is 20 min.

[0029] Preferably, in steps 3 and 4, the solution used for CV scanning is a 0.2 mol / L PBS solution with a pH of 7.0.

[0030] Preferably, in steps 3 and 4, the CV scanning range is -0.4V to 1.0V, and the scanning rate is 0.01V / s.

[0031] Preferably, in step 2, the incubation temperature of glucose oxidase at the sensing interface is 25°C, and the incubation time is 2 hours.

[0032] In this invention, step 1 provides a highly conductive Au-PB nanocomposite material to induce a rapid response at the sensing interface in step 2. Step 2 constitutes a biosensing interface that specifically recognizes glucose in sweat and facilitates electron transfer. The construction of the biosensing interface in step 2 is an essential key step in the electrochemical detection of glucose in sweat in steps 3 and 4. The working curve of glucose in sweat in step 3 provides a calculation basis for the determination of glucose concentration in artificial sweat in step 4. It can be seen that steps 1-4 support each other and work together to achieve the detection of glucose in sweat using the Au-PB-PEDOT composite material and glucose oxidase as recognition probes.

[0033] Compared with the prior art, the present invention has the following advantages:

[0034] This invention fully utilizes the properties of gold nanoparticles to enhance electron transport, as well as the effective current signal amplification and excellent load capacity of organic electrochemical transistors (OECTs), and combines them with high-affinity glucose oxidase to successfully fabricate a glucose oxidase sensor based on Au-PB-PEDOT nanocomposite materials, providing a new method for detecting glucose in sweat. This sensor exhibits good specificity, stability, and reproducibility. The detection of glucose in sweat using this invention is simple to operate, has good specificity, and offers high detection efficiency and sensitivity. Attached Figure Description

[0035] Figure 1 This is a schematic diagram of the principle of detecting glucose in sweat using an organic electrochemical transistor (OECT) sensor based on Au-PB-PEDOT.

[0036] Figure 2 This is a framework diagram of an organic electrochemical transistor (OECT) sensor detection system.

[0037] Figure 3A The IT curve for the first group of artificial sweat drops;

[0038] Figure 3B The IT curve for the second group after artificial sweat was applied;

[0039] Figure 4 The CV working curve for detecting 0.3 mM glucose in artificial sweat using a SiC potentiostat based on an Au-PB-PEDOT-GOx-based organic electrochemical transistor (OECT) sensor;

[0040] Figure 5 CV working curves for detecting 0.3 mM glucose in artificial sweat using an electrochemical workstation based on an Au-PB-PEDOT-GOx organic electrochemical transistor (OECT) sensor;

[0041] Figure 6 The CV working curves for detecting glucose concentration in artificial sweat are presented for three sets of Au-PB-PEDOT-GOx-based organic electrochemical transistor (OECT) sensors. Detailed Implementation

[0042] To make the objectives and advantages of the present invention clearer, the present invention will now be described in detail with reference to the accompanying drawings and embodiments.

[0043] This invention first deposits metallic gold onto the surface of an activated screen-printed electrode; then, PB and PEDOT are electrodeposited onto the electrode surface, and the composite material is fixed to the electrode surface through adsorption and chemical cross-linking; subsequently, glucose oxidase (GOD) is incubated, allowing GOD to covalently bind to Au-PB-PEDOT on the electrode surface, thus modifying the electrode. By detecting changes in the sensor's electrochemical signal using a colorimetric (CV) method, quantitative analysis of glucose in sweat can be effectively achieved.

[0044] like Figure 2 The diagram shows the framework of an organic electrochemical transistor (OECT) sensor detection system. The Au-PB-PEDOT-based OECT sensor is connected to the SIC4341 chip interface. Sweat samples are dropped onto the OECT sensor, and a smart device connects to the SIC4341 chip via NFC communication. After setting the parameters on the smart device, the detection is started, and the real-time monitoring results are displayed on the smart device screen as a CV curve after tens of seconds.

[0045] The present invention discloses a method for detecting glucose in sweat based on an organic electrochemical transistor sensor, the schematic diagram of which is shown below. Figure 1 As shown, the implementation steps are as follows:

[0046] Step 1: Preparation of materials such as GOx-PEDOT-PB-Au:

[0047] Weigh 0.157532 mg of chloroauric acid powder using a plastic spatula, add it to a brown glass bottle containing 200 ml of 2 mM sulfuric acid, and crush it with an ultrasonic crusher for 1 hour to dissolve it evenly. Then stir it with a constant temperature magnetic stirrer or a glass rod for 12 hours. Measure 2 ml of the 5.7 mM chloroauric acid solution and add 3 ml of deionized water to dilute it to prepare a 5 mM HAuCl4 solution.

[0048] Weigh 0.0745 g of potassium chloride powder into a beaker, add 10 mL of pure water, and stir until dissolved to prepare a potassium chloride solution. Weigh 0.0081102 g of ferric chloride powder into a beaker, add 10 mL of pure water, and stir until dissolved to prepare a ferric chloride solution. Weigh 0.008231 g of potassium ferricyanide powder into a beaker, add 10 mL of pure water, and stir until dissolved to prepare a potassium ferricyanide solution. Mix the prepared potassium chloride solution, ferric chloride solution, and potassium ferricyanide solution in equal proportions to obtain a Prussian blue (PB) solution. Then, take 2.0 mL of the Prussian blue solution for later use.

[0049] Pour 5 μL of poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate (PEDOT:PSS) solution into a container, add 5 mL of acetonitrile, and stir for 12 h using a thermostatic magnetic stirrer. Weigh 0.05 mg of 1 wt% chitosan and mix it evenly with 5 mL of 2 wt% acetic acid. Weigh 0.25 g of glucose oxidase (GOD) and mix it evenly with the prepared chitosan solution. Stir for 1 hour using a thermostatic magnetic stirrer. Record the current changes using an IT scan of a SiC4341 potentiostat from Silicon Process Technologies Co., Ltd., such as... Figure 3A , 3B As shown. Figure 3A The IT curve scanned after adding the first group of 0.3 mM artificial sweat shows that the appearance of the peak indicates successful specific recognition of glucose in sweat. Figure 3B The IT curves scanned after adding the second set of 0.3mM artificial sweat showed similar trends, indicating that GOx-PEDOT-PB-Au was relatively stably bound to the electrode.

[0050] Step 2: Electrode pretreatment: Before use, the SPE is first immersed in 0.5 mol / L H2SO4 solution for cyclic voltammetry scanning, scanning 20 segments within a voltage range of 0.5 V; after scanning, it is washed with pure water and dried to obtain activated SPE.

[0051] Step 3: Electrode Modification and Construction of Biosensing Interface: The activated SPE electrode was immersed in HAuCl4 solution and stirred with a magnetic stirrer. Deposition was carried out at a constant potential of 0.4V for 120s. After deposition, the electrode was washed three times with pure water and dried to obtain the Au / SPE electrode. The Au / SPE electrode was then immersed in 2.5% glutaraldehyde for 15min, followed by washing three times with PBS solution (pH 7.0) and pure water, and dried. Subsequently, 3μL of Prussian blue (PB) solution was added and the electrode was incubated in a shaking incubator for 30min. The electrode was then washed three times with PBS solution and pure water and dried to obtain PB-Au / SPE. 2 μL of 0.05 g / mL glucose oxidase solution was added dropwise to the PEDOT-PB-Au / SPE sensing interface and incubated in a shaking incubator for 2 h. Glucose oxidase that failed to immobilize at the interface was washed off, and 6 μL of 1% BSA solution was added for blocking. The sensor was then air-dried to obtain the GOx-PEDOT-PB-Au / SPE electrochemical glucose sensor. Current changes were recorded using a SiC4341 potentiostat from Silicon Process Technologies Co., Ltd., as shown in the figure. Figure 4As shown, the CV scan curve is obtained after the intelligent device starts detection after adding 0.3 mM artificial sweat to the Au-PB-PEDOT-based organic electrochemical transistor OECT sensor. The overall CV scan curve is similar to the standard curve scanned by the electrochemical workstation, which indicates that the glucose in the sweat specifically binds to the glucose oxidase on the electrode.

[0052] Step 4: Construction of the glucose standard curve: 2 μL of artificial sweat sample was added to the GOx-PEDOT-PB-Au / SPE sensing interface and incubated at 25°C for 20 min. The sample was then washed with PBS solution (pH 7.0) and pure water, and dried to obtain the working electrode. The obtained working electrode was then placed in 0.2 mol / L PBS buffer (pH 7.0), and its peak current was recorded using a CHI660E electrochemical workstation. Figure 5 .

[0053] Step 5: Repeated detection of glucose in multiple groups of artificial sweat: Artificial sweat samples with the same concentration of 0.3 mM were divided into three groups: Group I (no added substances), Group II (added with an equal concentration of lactic acid), and Group III (added with an equal concentration of uric acid). 2 μL of each sample was added to the surface of three glucose oxidase sensor electrodes prepared under identical conditions. Following the procedure in Step 4, three parallel measurements were performed using CV scanning to obtain the results. Figure 6 The three sets of CV curves for detecting glucose concentration in artificial sweat using the Au-PB-PEDOT-GOx-based organic electrochemical transistor (OECT) sensor are shown. Based on the standard curve from step 4, the glucose concentration in the corresponding artificial sweat sample can be calculated, as shown in Table 1.

[0054] Table 1. Detection results of glucose in actual artificial sweat.

[0055]

[0056] The above embodiments are merely specific examples to further illustrate the purpose, technical solution, and beneficial effects of the present invention, and the present invention is not limited thereto. Any modifications, equivalent substitutions, improvements, etc., made within the scope of the disclosure of the present invention are included within the protection scope of the present invention.

Claims

1. A method for detecting glucose in sweat based on an organic electrochemical transistor sensor, characterized in that, Includes the following steps: Step 1: Material Preparation (1) Preparation of chloroauric acid solution: Add chloroauric acid powder to a brown glass bottle containing sulfuric acid and stir until it is dissolved evenly. Measure out the chloroauric acid solution and dilute it with deionized water to obtain HAuCl4 solution. (2) Preparation of Prussian blue solution: Hydrochloric acid, potassium chloride, ferric chloride and potassium ferricyanide were mixed to prepare PB solution; (3) Preparation of poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate: Measure poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate and mix it evenly with acetonitrile, place it under a constant temperature magnetic stirrer and stir overnight to obtain PEDOT:PSS. Step 2: Electrode modification and construction of biosensing interface (1) Preparation of Au / SPE: The unactivated electrode was placed in a dilute sulfuric acid solution and cyclic voltammetry was performed to obtain the activated electrode SPE. The activated electrode was immersed in HAuCl4 solution and stirred under a magnetic stirrer for constant potential deposition. Then it was rinsed with pure water and dried to obtain the Au / SPE electrode. (2) Preparation of PB-Au / SPE sensing interface: Glutaraldehyde solution was placed in the Au / SPE electrode, rinsed with PBS solution and pure water, and dried. Add PB solution dropwise, perform potentiostatic deposition, rinse thoroughly with PBS solution and pure water, and blow dry to obtain the PB-Au / SPE sensing interface; (3) Construction of PEDOT-PB-Au / SPE electrochemical sensor: The prepared PB-Au / SPE sensing interface was placed in a poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate solution and stirred under a magnetic stirrer for constant potential deposition. Then, it was rinsed with pure water and dried to obtain the PEDOT-PB-Au / SPE sensing interface. Glucose oxidase solution was dropped onto the PEDOT-PB-Au / SPE sensing interface, placed in a shaking incubator for incubation, rinsed with water, and dried to obtain the GOx-PEDOT-PB-Au / SPE electrochemical sensor. Step 3: Plotting the working curve of sweat glucose (1) Add the standard artificial sweat solution to the GOx-PEDOT-PB-Au / SPE electrochemical sensor obtained in step 2, incubate, wash with PBS solution to obtain the working electrode, and air dry for later use; (2) The working electrode was placed in PBS solution and its peak current was recorded by CV scanning using an electrochemical workstation. (3) Test the glucose in sweat at different concentrations and plot the standard curve; Step 4: Detection of glucose in multiple artificial sweat samples (1) In the GOx-PEDOT-PB-Au / SPE electrochemical sensor obtained in step 2, add the same concentration of artificial sweat sample without additive, the same concentration of artificial sweat sample with added lactic acid, and the same concentration of artificial sweat sample with added uric acid respectively, incubate, wash with PBS solution to obtain 3 sets of working electrodes, and air dry for later use. (2) Place the working electrode in PBS solution, perform CV scan, and record its peak current; (3) The concentration of glucose in the artificial sweat to be tested is calculated based on the standard curve described in step 3.

2. The method for detecting glucose in sweat based on an organic electrochemical transistor sensor according to claim 1, characterized in that: The preparation process of the chloroauric acid solution in step 1 is as follows: Weigh 0.157532 mg of chloroauric acid powder with a plastic spatula, add it to a brown glass bottle containing 200 ml of 2 mM sulfuric acid, stir with a glass rod to dissolve it evenly, measure 2 ml of 5.7 mM chloroauric acid solution and add 3 ml of deionized water to dilute and prepare a 5 mM / L HAuCl4 solution.

3. The method for detecting glucose in sweat based on an organic electrochemical transistor sensor according to claim 1, characterized in that: The Prussian blue solution in step 1 is prepared by mixing 0.01M hydrochloric acid, 0.1M potassium chloride, 5mM ferric chloride, and 5mM potassium ferricyanide to form the Prussian blue solution.

4. The method for detecting glucose in sweat based on an organic electrochemical transistor sensor according to claim 1, characterized in that: The preparation process of poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate in step 1 is as follows: 5 μL of poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate is measured and mixed evenly with 5 mL of acetonitrile. The mixture is then placed under a constant temperature magnetic stirrer and stirred overnight to obtain a PEDOT:PSS solution.

5. The method for detecting glucose in sweat based on an organic electrochemical transistor sensor according to claim 1, characterized in that: In step 2, the working electrode is placed in 0.5 mol / L H2SO4 and subjected to 20 cyclic voltammetric scans with a voltage range of -0.2 V to 1.0 V.

6. The method for detecting glucose in sweat based on an organic electrochemical transistor sensor according to claim 5, characterized in that: In step 2(1), the HAuCl4 used has a mass fraction of 0.01%, a concentration of 1 mg / mL, a deposition potential of 0.4 V, and a deposition time of 120 s.

7. The method for detecting glucose in sweat based on an organic electrochemical transistor sensor according to claim 1, characterized in that: In steps 3 and 4, the incubation temperature of the working electrode is 25°C and the incubation time is 20 min.

8. The method for detecting glucose in sweat based on an organic electrochemical transistor sensor according to claim 1, characterized in that: In steps 3 and 4, the solution used for CV scanning was 0.2 mol / L PBS solution with a pH of 7.

0.

9. The method for detecting glucose in sweat based on an organic electrochemical transistor sensor according to claim 1, characterized in that: In steps 3 and 4, the CV scan range is -0.4V to 1.0V, and the scan rate is 0.01V / s.

10. The method for detecting glucose in sweat based on an organic electrochemical transistor sensor according to claim 1, characterized in that: In step 2, the glucose oxidase is incubated at the sensing interface at a temperature of 25°C for 2 hours.

Images