Electrochemical electrode, continuous glucose monitoring sensor and preparation method therefor

Abstract

Provided in the present invention are a flexible electrochemical electrode, a subcutaneous continuous glucose monitoring sensor equipped with the electrochemical electrode, and a preparation method thereof. The electrode directly uses gold layers on both sides of a chemically plated film, respectively as a working electrode and a reference-counter electrode, so as to form an electrochemical two-electrode system. Petaloid platinum nanoparticles are electrodeposited on a surface of the configured working electrode as a catalytic layer; a carbon nanotube/Nafion mesh layer functions as an anti-interference layer, and is formed thereon with an enzyme biochemical sensitive layer by means of electrostatic adsorption, after crosslinking and curing in glutaraldehyde, polyurethane mass transfer is coated to limit a protection layer, so as to prepare a flexible continuous glucose monitoring sensor. The sensor does not require photolithography, screen printing or other technologies to construct an electrochemical electrode system. The present invention effectively simplifies the processing technology, can easily achieve large-scale production and reduce production costs; and meanwhile, the present invention has characteristics such as a wide linear range, low detection limit, powerful anti-interference capacity, high response sensitivity and long-term stability.

Claims

1. An electrochemical electrode, comprising an electrode matrix (1) made of a polymer film, and two sides of the electrode matrix (1) comprising a conductive layer deposited by a surface metallization technology, the two conductive layers being used as a working electrode and a reference-counter electrode respectively; wherein the working electrode comprises a platinum black layer (3); a carbon nanotube/Nafion mesh layer (4); an enzyme biochemical sensitive layer (5).

2. The electrode according to claim 1, wherein the working electrode further comprises a polyurethane protection layer.

3. The electrode according to claim 1, wherein there is a bonding layer between the conductive layer and the film layer, and the bonding layer is a polydopamine layer.

4. The electrode according to claim 1, wherein the working electrode sequentially comprises from the inside out a platinum black layer; a carbon nanotube/Nafion mesh layer; an enzyme biochemical sensitive layer and a polyurethane protection layer.

5. The electrode according to claim 1, wherein the reference-counter electrode comprises a platinum layer and a polyurethane protection layer covered by a gold layer (20) respectively.

6. The electrochemical electrode according to claim 1, wherein the electrode comprises a through hole extending through the film.

7. The electrochemical electrode according to claim 6, wherein the through hole (9) on the electrode is a circular hole, a square hole or an interdigitated comb hole.

8. The electrochemical electrode according to claim 6, wherein the number of through holes (9) on the electrode can be arbitrarily combined.

9. The electrochemical electrode according to claim 1, wherein the thickness of the polymer film is 20 m to 200 m; the thickness of the conductive layer (2, 20) on both sides of the electrode matrix (1) is at least 5 m.

10. The electrochemical electrode according to claim 1, wherein the conductive layer is a gold layer.

11. A continuous glucose monitoring sensor, comprising an electrochemical electrode and a lead base as claimed in claim 1, wherein the electrode has a fine needle shape.

12. A continuous glucose monitoring sensor, comprising the fine needle-shaped electrode of claim 11 having a diameter of no more than 0.3 mm.

13. The continuous glucose monitoring sensor according to claim 12, wherein the through hole (9) on the electrode is a circular hole, a square hole or an interdigitated comb hole.

14. The continuous glucose monitoring sensor according to claim 13, wherein the through hole (9) on the electrode has a diameter/width of not more than 0.15 mm.

15. A method of making a sensor, comprising the following steps: {circle around (1)} Providing a film material; {circle around (2)} Depositing a polydopamine layer on the surface of the film material; {circle around (3)} Depositing a catalytic layer on the surface of the film material; {circle around (4)} Chemically depositing a gold layer on the surface of the film material; {circle around (5)} Adsorbing a carbon nanotube mesh layer on the surface of the film material.

16. The method according to claim 15, wherein the film material is subjected to decontamination, and the treatment method comprises the following steps: cutting a polymer film material having a thickness of at least 20 m into sheets respectively, placing them in an organic solvent, such as acetone and ethanol; and performing ultrasonic treatment in deionized water for 5 minutes and drying, then removing oil dirt on the surface.

17. The method according to claim 15, wherein the method for depositing a polydopamine layer on the surface of the film material: immersing the cleaned sheet in a dopamine hydrochloride solution (pH 8.5, 2 mg/ml), placing it on a bleaching shaker at room temperature, and after oxidizing in air for 24 hours, a layer of polydopamine is formed on the surface of the sheet, after immersed and cleaned in deionized water for 8 hours, dried in a 80 C. oven.

18. The method according to claim 15, wherein the method of depositing a catalytic layer on the surface of the film material comprises the following steps: immersing the dried sheet in a 0.1 wt % Stearyl Trimethyl Ammonium Chloride (STAC) solution for 5 s, and taking out for drying, then placing it in platinum nanosol for 30 min, adsorbing a platinum nanoparticle layer on the surface of the sheet, and taking out, gently rinsing the surface with deionized water, to remove the unimmobilized platinum nanoparticles and dry.

19. The method according to claim 15, wherein chemically depositing the gold layer on the surface of the film material comprises the following steps: placing the dried sheet into a gold plating liquid (containing 10 mM chloroauric acid and 20 mM hydrogen peroxide) for 15 minutes, and then quickly placing in a 120 C. oven for annealing for 50 min, and turning off the oven, when the temperature in the oven has dropped to room temperature, taking out the sheet, at this time, a layer of bright, compact and firm gold is deposited on the surface of the sheet.

20. The method according to claim 15, wherein adsorbing a carbon nanotube mesh layer on the surface of the film material: immersing the electrode in aqueous dispersion liquid of carbon nanotube (carbon nanotube aqueous dispersion liquid:5 wt % Nafion=1:4), setting a working voltage of 1 V and a working time of 10 s by the potentiostatic method, to form a carbon nanotube mesh layer on the outer peripheral surface of the working electrode hole.

21. The method according to claim 15, further comprising the steps of electrodepositing a platinum layer on the surface of the film material: placing the cleaned gold-plated electrode on a platinum plating solution (3 wt % chloroplatinic acid, 0.25 wt % lead acetate), and setting the working potential at 2.5 V and the deposition time at 120 s by the constant-voltage method using platinum filament as a counter electrode; electrodepositing a compact platinum black layer on both sides of the electrode simultaneously, and sputtering or coating an insulating layer (8) on both sides of the sheet.

22. The method according to claim 15, wherein the steps 2 to 4 are performed sequentially.

23. The method according to claim 15, wherein the film layer can be subjected to one or more of the following treatments: parylene insulation treatment: Sputtering or coating a Parylene insulating layer on both sides of the sheet; or, boring to form a working surface: Making a through hole (9) by laser on the surface of the set electrode working area to form a working area; or, crosslinking and curing: overhanging the electrode in a container with 25% glutaraldehyde at the bottom, cross-linked in a 40 C. oven for 60 min, and storing in a refrigerator at 4 C. for 2 h to firmly bond the carbon nanotube mesh layer with the substrate; or, electro-adsorbing GOx enzyme layer: immersing the working part of the electrode in the GOx enzyme solution (BSA:GOx=1:3, concentration of 30 mg/ml), setting the working voltage at 0.3V and the working time at 2400 s by the potentiostatic method using the side of the carbon nanotube mesh layer as the working electrode and the other side as the counter electrode, then storing the electrode in a 4 C. refrigerator for 8 h, so that GOx is fully embedded in the carbon nanotube mesh layer to form the GOx enzyme layer; or, cutting electrode: cutting the sheet into a filament-like, single-layer double-sided electrode using an ultraviolet laser cutting machine; or, forming a polyurethane protection layer: dissolving 4 wt % of polyurethane in a mixed solution of 98 v % tetrahydrofuran and 2 v % dimethylformamide to form a polyurethane solution, slowly passing the electrode sensing portion through a steel wire ring with an inner diameter of 2 mm soaked with the polyurethane solution, to form a polyurethane protection layer on the surface of the electrode; or, assembling an electrode: fixing the electrode tail end to the base, and the lead wire area (7) on the electrode tail end is electrically connected to the sensing component in the base.

24. A method of making a sensor, comprising the following steps: {circle around (1)} PI slice decontamination: cutting a polymer film material having a thickness of at least 20 m into a sheet, and placing them in acetone, ethanol, deionized water for ultrasonic treatment for 5 min and drying, to remove the oil dirt on the surface; {circle around (2)} depositing polydopamine layer: immersing the cleaned sheet in a dopamine hydrochloride solution (pH 8.5, 2 mg/ml), placing it on a bleaching shaker at room temperature, and after oxidizing in air for 24 hours, a layer of polydopamine is formed on the surface of the sheet, after immersed and cleaned in deionized water for 8 hours, dried in a 80 C. oven; {circle around (3)} depositing catalytic layer: immersing the dried sheet in a 0.1 wt % Stearyl Trimethyl Ammonium Chloride (STAC) solution for 5 s, and taking out for drying, then placing it in platinum nanosol for 30 min, adsorbing a platinum nanoparticle layer on the surface of the sheet, and taking out, gently rinsing the surface with deionized water, to remove the unimmobilized platinum nanoparticles and dry; {circle around (4)} chemically depositing gold layer: placing the dried sheet into a gold plating liquid (containing 10 mM chloroauric acid and 20 mM hydrogen peroxide) for 15 minutes, and then quickly placing in a 120 C. oven for annealing for 50 min, and turning off the oven, when the temperature in the oven has dropped to room temperature, taking out the sheet, at this time, a layer of bright, compact and firm gold is deposited on the surface of the sheet; {circle around (5)} electrodepositing platinum layer: placing the cleaned gold-plated electrode on a platinum plating solution (3 wt % chloroplatinic acid, 0.25 wt % lead acetate), and setting the working potential at 2.5 V and the deposition time at 120 s by the constant-voltage method using platinum filament as a counter electrode; electrodepositing a compact platinum black layer on both sides of the electrode simultaneously, and sputtering or coating an insulating layer (8) on both sides of the sheet; {circle around (6)} parylene insulation treatment Sputtering or coating a Parylene insulating layer on both sides of the sheet; {circle around (7)} boring to form a working surface making a through hole (9) by laser on the surface of the set electrode working area to form a working area; {circle around (8)} adsorbing carbon nanotube mesh layer: immersing the electrode in aqueous dispersion liquid of carbon nanotube (carbon nanotube aqueous dispersion liquid:5 wt % Nafion=1:4), setting a working voltage of 1 V and a working time of 10 s by the potentiostatic method, to form a carbon nanotube mesh layer on the outer peripheral surface of the working electrode hole; {circle around (9)} crosslinking and curing: overhanging the electrode in a container with 25% glutaraldehyde at the bottom, cross-linked in a 40 C. oven for 60 min, and storing in a refrigerator at 4 C. for 2 h to firmly bond the carbon nanotube mesh layer with the substrate; {circle around (10)} electro-absorbing GOx enzyme layer: immersing the working part of the electrode in the GOx enzyme solution (BSA:GOx=1:3, concentration of 30 mg/ml), setting the working voltage at 0.3V and the working time at 2400 s by the potentiostatic method using the side of the carbon nanotube mesh layer as the working electrode and the other side as the counter electrode, then storing the electrode in a 4 C. refrigerator for 8 h, so that GOx is fully embedded in the carbon nanotube mesh layer to form the GOx enzyme layer; {circle around (11)} cutting electrode: cutting the sheet into a filament-like, single-layer double-sided electrode using an ultraviolet laser cutting machine; {circle around (12)} forming a polyurethane protection layer: dissolving 4 wt % of polyurethane in a mixed solution of 98 v % tetrahydrofuran and 2 v % dimethylformamide to form a polyurethane solution, slowly passing the electrode sensing portion through a steel wire ring with an inner diameter of 2 mm soaked with the polyurethane solution, to form a polyurethane protection layer on the surface of the electrode; {circle around (13)} assembling an electrode: fixing the electrode tail end to the base, and the lead wire area (7) on the electrode tail end is electrically connected to the sensing component in the base.

25. The method according to claim 24, wherein the method of preparing platinum nanosol in the step {circle around (3)} is as follows: dissolving 0.25 mmol of chloroplatinic acid in 91.5 ml of water, dissolving 5 mg of PVP in 5 ml of water and adding to the chloroplatinic acid solution, then dissolving 1 mmol of sodium borohydride in 10 ml of water, taking 1 ml and slowing adding to the mixed solution of PVP and chloroplatinic acid, after shaking vigorously, standing at room temperature for 24 hours.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0046] FIG. 1A is a cross-sectional structural view of an electrochemical electrode according to an embodiment of the present invention; FIG. 1B is a cross-sectional structural view of an electrochemical electrode according to another embodiment of the present invention; FIG. 1C is a top view of an electrochemical electrode according to another embodiment of the present invention; FIG. 1D is a schematic flow chart of an electrochemical electrode according to another embodiment of the present invention.

[0047] FIG. 2 is a schematic perspective view of an electrochemical electrode of the present invention;

[0048] FIG. 3 is a schematic perspective structural view of an electrochemical electrode according to a second embodiment of the present invention;

[0049] FIG. 4 is a schematic perspective structural view of an electrochemical electrode according to a second embodiment of the present invention;

[0050] FIG. 5A is a flow chart of a process for preparing a continuous glucose monitoring sensor according to an embodiment of the present invention; FIG. 5B is a flow chart of a process for preparing a continuous glucose monitoring sensor according to another embodiment of the present invention.

[0051] FIG. 6 is a data analysis graph of glucose monitoring performance test of the sensor of the present invention;

[0052] FIG. 7 is a data analysis graph of anti-interference test of uric acid, ascorbic acid and ibuprofen of the sensor of the present invention.

[0053] FIG. 8 shows a response change process of the sensor prepared according to the embodiments of the present invention from 0 mM to 3 mM.

DETAILED DESCRIPTION

[0054] In order to make the technical solution of the present invention clearer, the present invention will be described in detail below with reference to FIGS. 1 to 5. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the scope of the invention.

Example 1

[0055] Referring to FIGS. 1 and 2, an electrochemical electrode whose electrode matrix 1 is made of polymer film (PI) (illustrated by source or manufacturer), PI has a thickness of 20 m to 200 m, preferably a thickness of at least 20 m; and both sides of electrode matrix 1 are deposited a gold layers 2 (the gold layer serves as an electrode, and any other metal can be used as a conductor) and 20 by the surface metallization technology, and the gold layers 2, 20 on both sides of the electrode matrix 1 has a thickness of at least 5 m, and the two gold layers 2 and 20 serve as a working electrode A and a reference-counter electrode B respectively; the working electrode A is covered by a platinum black layer 3, a carbon nanotube/Nafion mesh layer 4, an enzyme biochemical sensitive layer 5, a polyurethane protection layer 6 respectively from the gold layer 2 to the outside; and the reference-counter electrode B is covered by a platinum black layer 30 and a polyurethane protection layer 60 respectively from gold layer 20 to outside. The electrode matrix 1 is provided with a through hole 9 that passes through the polyurethane protection layers 6 and 60 on both sides, and the through hole 9 is a circular hole, and the circular hole is coated with a hydrophilic polymer layer.

[0056] Surface metallization technology is a prior art. In recent years, bionics studies have shown that, dopamine can undergo oxidative polymerization under aqueous conditions, forming a strong adhesive composite layer on a series of solid materials such as polymers, metals, ceramics, glass, and woods, etc., while the catechol group of dopamine can exert a certain binding force on the metal, and the polydopamine composite layer has strong reducing ability to metal ions; when the modification materials deposited with a polydopamine layer on the surface are immersed in the metal salt solution, the composite layer reduces metal cations from the solution and deposits them on the surface of the material, to achieve the surface metallization of the electroless materials.

Example 1-2

[0057] On the basis of Example 1 and referring to FIG. 3, the electrode matrix 1 is provided with a square hole 91 passing through the polyurethane protective layers 6 and 60 on both sides, and the square hole 91 is coated with a hydrophilic polymer layer.

Example 1-3

[0058] On the basis of Example 1 and referring to FIG. 4, the electrode matrix 1 is provided with a through hole 92 passing through the polyurethane protective layers 6 and 60 on both sides. The through hole 92 has a cross section of interdigitated comb shape, and the through hole 92 is coated with a hydrophilic polymer layer.

Example 2

[0059] On the basis of Example 1, a continuous glucose monitoring sensor comprises a base and an electrochemical electrode described in the Example 1. The electrochemical electrode is disposed below the base, and the tip of the electrode is needle-shaped, and the electrode tail end is vertically fixed to the base. The needle-shaped electrode can be directly implanted into the subcutaneous tissues. As it is a single-sheet double-sided electrode structure, it has small implantation trauma; in addition, it effectively simplifies the processing technology and reduces the production cost. The base may be further provided with a wireless transmission device, which converts the monitoring data of the sensor into signals and outputs them to an external cloud data management module for storage. Through the cloud data management module, the data and values are monitored in a real-time manner. The cloud data management module may be a computer, a handset, a table PC, etc.

Example 3

[0060] On the basis of Embodiments 1 and 2 and referring to FIG. 5, a method for preparing a continuous glucose monitoring sensor according to the embodiment 2, comprising the following steps:

[0061] {circle around (1)} PI slice decontamination: cutting a polymer film material having a thickness of 120 m into a sheet, and placing them in acetone, ethanol, deionized water for ultrasonic treatment for 5 min and drying, to remove the oil dirt on the surface;

[0062] {circle around (2)} depositing polydopamine layer: immersing the cleaned sheet in a dopamine hydrochloride solution (pH 8.5, 2 mg/ml), placing it on a bleaching shaker at room temperature, and after oxidizing in air for 24 hours, a layer of polydopamine is formed on the surface of the sheet, after immersed and cleaned in deionized water for 8 hours, dried in a 80 C. oven

[0063] {circle around (3)} depositing catalytic layer: immersing the dried sheet in a 0.1 wt % Stearyl Trimethyl Ammonium Chloride (STAC) solution for 5 s, and taking out for drying, then placing it in platinum nanosol for 30 min, adsorbing a randomly distributed platinum nanoparticle layer on the surface of the sheet as a catalytic layer, and taking out, gently rinsing the surface with deionized water, to remove the unimmobilized platinum nanoparticles and dry;

[0064] The method of preparing platinum nanosol is as follows: dissolving 0.25 mmol of chloroplatinic acid in 91.5 ml of water, dissolving 5 mg of PVP in 5 ml of water and adding to the chloroplatinic acid solution, then dissolving 1 mmol of sodium borohydride in 10 ml of water, taking 1 ml and slowing adding to the mixed solution of PVP and chloroplatinic acid, after shaking vigorously, standing at room temperature for 24 hours.

[0065] {circle around (4)} chemically depositing gold layer: placing the dried sheet into a gold plating liquid (containing 10 mM chloroauric acid and 20 mM hydrogen peroxide) for 15 minutes, and then quickly placing in a 120 C. oven for annealing for 50 min, and turning off the oven, when the temperature in the oven has dropped to room temperature, taking out the sheet, at this time, a layer of bright, compact and firm gold is deposited on the surface of the sheet, with a thickness of about 10 m;

[0066] {circle around (5)} Electrodepositing platinum layer: placing the cleaned gold-plated electrode on a platinum plating solution (3 wt % chloroplatinic acid, 0.25 wt % lead acetate), and setting the working potential at 2.5 V and the deposition time at 120 s by the constant-voltage method using platinum filament as a counter electrode; electrodepositing a compact platinum black layer on both sides of the electrode simultaneously, and sputtering or coating an insulating layer (8) on both sides of the sheet;

[0067] {circle around (6)} Parylene insulation treatment

[0068] Sputtering or coating a Parylene insulating layer on both sides of the sheet;

[0069] {circle around (7)} boring to form a working surface

[0070] Making a through hole (9) by laser on the surface of the set electrode working area to form a working area, and setting the pore size at 0.12 mm;

[0071] {circle around (8)} Adsorbing carbon nanotube mesh layer: immersing the electrode in aqueous dispersion liquid of carbon nanotube (carbon nanotube aqueous dispersion liquid:5 wt % Nafion=1:4), setting a working voltage of 1 V and a working time of 10 s by the potentiostatic method, to form a carbon nanotube mesh layer on the outer peripheral surface of the working electrode hole.

[0072] {circle around (9)} crosslinking and curing: overhanging the electrode in a container with 25% glutaraldehyde at the bottom, cross-linked in a 40 C. oven for 60 min, and storing in a refrigerator at 4 C. for 2 h to firmly bond the carbon nanotube mesh layer with the substrate

[0073] {circle around (10)} Electro-absorbing GOx enzyme layer: dissolving a mixed powder of 300 mg of bovine serum albumin (BSA) and 1 g of glucose oxidase (GOx) in 40 ml of deionized water to form a GOx enzyme solution, immersing the electrode in the GOx enzyme solution, setting the working voltage at 0.3V and the working time at 2400 s by the potentiostatic method using the side of the carbon nanotube mesh layer as the working electrode and the other side as the counter electrode, then electro-adsorbing GOx to the working electrode, then storing the electrode in a 4 C. refrigerator for 8 h, so that GOx is fully embedded in the carbon nanotube mesh layer, finally, after cross-linking for 40 min with the cross-linking and curing method described in step {circle around (9)}, storing the mixture in a 4 C. refrigerator for 8 h, so that the enzyme layer is fully crosslinked and cured, and then rinsing off the insufficiently immobilized enzyme with deionized water;

[0074] {circle around (11)} Cutting electrode: cutting the sheet into a filament-like, single-layer double-sided electrode using an ultraviolet laser cutting machine, and setting the size of the implanted part at 0.25 mm5 mm;

[0075] {circle around (12)} Forming a polyurethane protection layer: dissolving 4 wt % of polyurethane in a mixed solution of 98 v % tetrahydrofuran and 2 v % dimethylformamide to form a polyurethane solution, slowly passing the electrode sensing portion through a steel wire ring with an inner diameter of 2 mm soaked with the polyurethane solution, to form a polyurethane protection layer on the surface of the electrode;

[0076] {circle around (13)} Assembling an electrode: fixing the electrode tail end to the base, and the lead wire area (7) on the electrode tail end is electrically connected to the sensing component in the base.

[0077] The electrode prepared in the above steps {circle around (1)} to {circle around (13)} can be placed in a drying oven at 25 C. for future use if it needs to be stored.

[0078] For the sensor electrode prepared by the method, the gold layer is tightly bound with the surface of the PI, and the gold nanoparticles are neat, compact and evenly distributed. The gold layer has high uniformity and compactness, and compared with the gold layer formed by other processing technologies, the gold layer can be subjected to the electrochemical deposition of platinum and other functional modifications on its surface, without producing peel-off or falling off of the metal layer and the non-metal layer over the deposition time (explained or demonstrated by experimental data?) Furthermore, as the electrode working surface is a gold/platinum layer having a thickness of about 10-15 m at the edge of the circular hole, the micron-scale electrode structure effectively enhances the mass transfer performance and enhances the electrochemical reaction performance. The combined through hole structure and carbon nanotube porous structure has the effect of increasing the enzyme loading capacity and protecting the enzyme activity, and enhancing the long-term stability of the sensor (explained or demonstrated by experimental data?)

[0079] Glucose continuous response test: Inject 10 ml of blank PBS solution (pH 7.2) into the detection cell, place the detection cell on the magnetic stirrer platform, to keep the heating surface of the magnetic stirrer at (37 C.2 C.) for at least 5 min, and maintain the detection cell temperature at 37 C.2 C. and the magnet speed at 200 rpm. Immerse the sensor 5 mm below the surface of the solution in the detection chamber and conduct a continuous response test using a chronoamperometry (i-t). The constant voltage potential is set at 0.3V. After power-on and initialization for more than 40 min, inject a certain amount of glucose solution to the detection cell, so that the glucose concentration in the detection cell continuously rises from 0 to 33 mM, as shown in FIG. 6. FIG. 7 shows the linearity of the sensor, and FIG. 8 shows the response change process from 0 mM to 3 mM. As shown from the figures, the sensor has a wide linear response range, and its linearity is over 99% and sensitivity is up to 100 Acm2(mmol/L)1 in the range of 030 mM. The sensor also has a fast response speed. Considering the effect of each injection of glucose on the concentration equilibrium time of the detection cell, the response time of each gradient concentration change is within the range of 1530 s and the average response time is about 25 s.

[0080] FIG. 9 shows the data analysis chart of anti-interference tests of ascorbic acid, uric acid and acetaminophen on the sensor, wherein, a. 4.0 mmol/L glucose; b. 0.1 mmol/L ascorbic acid; c. 0.5 mmol/L uric acid d. 0.2 mmol/L acetaminophen; e. 4.0 mmol/L glucose; f. 4.0 mmol/L glucose. As shown from the figure, the glucose monitoring sensor in the present invention has good anti-interference to uric acid, ascorbic acid and acetaminophen, and it has a porous inner layer of Nafion/carbon nanotube network, playing a positive role for the anti-interference of the sensor. In addition, the sensor structure has a close gap between the working electrode and the reference-counter electrode, so that the sensor can still exhibit a better detection range and linear range at an operating voltage below 0.5V.

[0081] For the glucose monitoring sensor in the present invention, the enzyme layer is dissolved in a porous network structure formed by the Nafion/carbon nanotubes, which greatly increases the enzyme load, reduces the opportunity for glucose molecules to enter the electrode layer directly and effectively promotes the stability of the response current.

[0082] All patents and publications mentioned in the specification of the present invention are disclosed art and can be used in the present invention. All patents and publications cited herein are incorporated by reference as they are cited as reference separately. The invention described herein can be achieved in the absence of any element or elements, a limitation or limitations, and such limitations are not specifically described herein. For example, the terms comprising, essentially consisting of and consisting of in each of the examples herein may be replaced with the remaining two terms of either. The terms and expressions used herein are illustrative rather than limitation, and they are not intended to exclude any equivalent features of these terms and expressions described herein, however, it should be aware that any appropriate changes or modifications within the scope of the invention and claims may be made. It should be understood that the embodiments of the present invention are described in the preferred embodiments of the present invention, and that various modifications and changes can be made by those skilled in the art in accordance with the teachings of the present invention. These modifications and changes should be considered to fall into the scope of the invention and the scope of the independent claims and the appended claims.