CN211785300U

CN211785300U - Working electrode of glucose monitoring probe

Info

Publication number: CN211785300U
Application number: CN202020454895.7U
Authority: CN
Inventors: 方骏飞; 郭盼; 韩明松; 夏斌; 赵瑜
Original assignee: Shenzhen Guiji Sensing Technology Co ltd
Current assignee: Shenzhen Guiji Sensing Technology Co ltd
Priority date: 2019-06-24
Filing date: 2020-03-31
Publication date: 2020-10-27
Anticipated expiration: 2030-03-31
Also published as: CN116473552A; CN116807469A; CN111248924A; CN111248924B

Abstract

The utility model relates to a working electrode of a glucose monitoring probe, which comprises a basal layer formed on a flexible substrate; the sensing layer is formed on the substrate layer by coating a sensing layer reagent and can chemically react with glucose, the sensing layer reagent comprises a metal polymer, glucosaccharase, carbon nanotubes and a cross-linking agent, the carbon nanotubes are in a hollow column shape and adsorb the metal polymer and the glucosaccharase, amino modification is added to the carbon nanotubes in the sensing layer reagent, and the metal polymer is combined with the carbon nanotubes through covalent bonds; a semi-permeable membrane formed on the sensing layer to control the passage rate of glucose molecules; and a biocompatible membrane formed on the semi-permeable membrane. According to the utility model discloses, can reduce working electrode operating voltage, reduce and disturb, prolong glucose monitor probe's life to improve the reaction sensitivity to glucose.

Description

Working electrode of glucose monitoring probe

Technical Field

The utility model relates to a glucose monitor field, concretely relates to working electrode of glucose monitoring probe.

Background

Biosensors are analytical devices that tightly bind biological, biologically derived, or biomimetic materials to optical, electrochemical, temperature, piezoelectric, magnetic, or micromechanical physicochemical sensors or sensing microsystems. To date, the most commercially successful biosensor used is the amperometric enzyme glucose sensor. The market share of amperometric enzyme glucose sensors occupies almost 85% of today's global market. Amperometric enzyme glucose sensors are used to detect diabetes, and the larger the market share, the more people with diabetes are reflected.

Diabetes is a series of metabolic disorder syndromes of sugar, protein, fat, water, electrolyte and the like, and is caused by hypofunction of pancreatic islets, insulin resistance and the like caused by the action of various pathogenic factors such as genetic factors, immune dysfunction, microbial infection and toxins thereof on organisms. If diabetes is not well controlled, complications such as ketoacidosis, lactic acidosis, chronic renal failure and retinopathy may arise. With the increasing incidence of diabetes, diabetes has become a public health problem worldwide.

At present, no radical cure method is available for diabetes, and only a control method is available. For diabetic patients, if the patients can monitor glucose continuously in real time on a daily basis, the occurrence of complications such as low glucose and high glucose in insulin-dependent diabetic patients can be reduced and reduced preferentially.

Typically, glucose monitoring is accomplished by a glucose meter in an amperometric enzyme glucose sensor. The sensing probe of a glucose meter is generally implanted in the body to monitor the glucose concentration in interstitial fluid and the rate of change of the glucose concentration in the surrounding blood flow, metabolism and blood vessels. Studies have shown that glucose concentration changes in interstitial fluid are generally delayed from glucose concentration changes in blood by 2-45 minutes with an average delay of about 6.7 minutes. However, when the glucose concentration in the blood begins to decrease, the glucose concentration in the interstitial fluid first decreases compared to the glucose concentration in the blood, indicating that a decrease in glucose concentration in the interstitial fluid can be predicted for an impending low glucose.

With the development of the technological level, various portable glucose monitors are introduced into the eyes of people, and especially some implantable continuous glucose monitoring devices are favored by diabetics and hospitals. However, implantable continuous glucose meters tend to have a short lifetime and are susceptible to immune reactions in the body and to other impurities in the blood that reduce sensitivity. Therefore, how to better construct the detection device, prolong the service life of the sensing probe of the glucose detector and reduce the influence of other factors becomes the biggest problem at present.

SUMMERY OF THE UTILITY MODEL

The present invention has been made in view of the above circumstances, and an object of the present invention is to provide a working electrode of a glucose monitoring probe, which can prolong the service life of the probe, reduce interference, and improve the sensitivity of the reaction to glucose.

Therefore, an aspect of the present invention provides a working electrode of a glucose monitoring probe, which is characterized in that: a base layer formed on a flexible substrate; a sensing layer formed on the base layer by coating a sensing layer reagent, the sensing layer reagent being capable of chemically reacting with glucose, the sensing layer reagent including a metal polymer, a glucosidase, a carbon nanotube and a cross-linking agent, the carbon nanotube having a hollow columnar shape, the carbon nanotube adsorbing the metal polymer and the glucosidase, the sensing layer reagent including an amino group modification added to the carbon nanotube, the metal polymer being covalently bonded to the carbon nanotube; a semi-permeable membrane formed on the sensing layer, controlling the passage rate of glucose molecules; and a biocompatible membrane formed on the semi-permeable membrane.

In the working electrode of the glucose monitoring probe according to an aspect of the present invention, the sensing layer includes a carbon nanotube. Under the condition, the catalytic action of the carbon nano tube on the glucose reaction reduces the working voltage required by the normal work of the working electrode, and reduces the interference of the current generated by the electrochemical reaction of the electroactive substances under partial high voltage on the working electrode; meanwhile, the reaction sensitivity of the probe to glucose is improved, the linear range of the response of the probe to the glucose is enlarged, and the service life of the probe is prolonged.

Further, in a working electrode of a glucose monitoring probe according to an aspect of the present invention, optionally, the semipermeable membrane includes a diffusion control layer for controlling diffusion of glucose molecules. In this case, when glucose molecules in interstitial fluid or blood enter the semipermeable membrane, the number of glucose molecules is reduced in a certain proportion, so that when glucose reacts with the sensing layer, the sensing layer is in an excessive state, the glucose concentration becomes the only factor for limiting the current of the working electrode, and the linear range of the glucose monitoring probe in monitoring the glucose concentration is expanded.

Additionally, in a working electrode of a glucose monitoring probe according to an aspect of the present invention, optionally, the semipermeable membrane includes an anti-interference layer that blocks non-glucose substances. In this case, other components in the interstitial fluid or blood are prevented from entering the semipermeable membrane, and the influence of other electroactive substances which can also generate current on the working electrode, which results in inaccurate glucose detection results, is avoided.

Further, in the working electrode of the glucose monitoring probe according to an aspect of the present invention, optionally, the sensing layer has a thickness of 0.1 μm to 100 μm. This makes it possible to provide sufficient glucosidase while ensuring sufficient reaction and firm adhesion.

Further, in a working electrode of a glucose monitoring probe according to an aspect of the present invention, optionally, the probe has a lifetime of 1 to 24 days. Therefore, patients with different requirements can conveniently select corresponding service lives.

According to the utility model discloses, can provide the life of an extension probe, reduce the interference and improve the working electrode of glucose monitoring probe to the reaction sensitivity of glucose and manufacturing method thereof.

Drawings

Fig. 1 is a schematic view showing a state of use of a glucose monitoring probe according to an embodiment of the present invention.

Fig. 2 is a schematic configuration diagram showing a glucose monitoring probe according to an embodiment of the present invention.

FIG. 3 is a schematic diagram showing the glucose monitoring probe of FIG. 2 in a bent state.

Fig. 4 is a schematic configuration diagram showing the working electrode of the glucose monitoring probe according to the embodiment of the present invention.

Fig. 5 is a schematic diagram showing that the carbon nanotube of the glucose monitoring probe according to the embodiment of the present invention adsorbs glucosidase.

Fig. 6 is a schematic diagram showing a glucose reaction between a glucose monitoring probe and a tissue according to an embodiment of the present invention.

Fig. 7 is a schematic structural view showing a semipermeable membrane of a working electrode of a glucose monitoring probe according to an embodiment of the present invention.

Fig. 8 is a flowchart illustrating a method for manufacturing a working electrode of a glucose monitoring probe according to an embodiment of the present invention.

Fig. 9 is a flowchart illustrating a method for manufacturing a semipermeable membrane for a working electrode of a glucose monitoring probe according to an embodiment of the present invention.

Detailed Description

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings. In the following description, the same components are denoted by the same reference numerals, and redundant description thereof is omitted. The drawings are schematic and the ratio of the dimensions of the components and the shapes of the components may be different from the actual ones.

In addition, the headings and the like referred to in the following description of the present invention are not intended to limit the content or scope of the present invention, but only serve as a reminder for reading. Such a subtitle should neither be understood as a content for segmenting an article, nor should the content under the subtitle be limited to only the scope of the subtitle.

Fig. 1 is a schematic view showing a state of use of a glucose monitoring probe according to an embodiment of the present invention. Fig. 2 is a block diagram showing a glucose monitoring probe according to an embodiment of the present invention. FIG. 3 is a schematic diagram showing the glucose monitoring probe of FIG. 2 in a bent state.

In the present embodiment, the glucose monitoring probe 1 may also be referred to as an implantable glucose monitoring probe 1, a probe 1 of a glucose monitor, or a probe 1.

In this embodiment, the portable glucose monitor G may include a glucose monitoring probe 1 and an electronic system 2 connected to the glucose monitoring probe 1. Through implanting the glucose monitoring probe 1 with portable glucose monitor G to the human body such as the body surface of human body, glucose monitoring probe 1 contacts with the interstitial fluid or the blood of body surface to can utilize glucose monitoring probe 1 sensing interstitial fluid's the sensing signal correlated with glucose concentration, through giving electronic system 2 with this glucose concentration signal transmission, thereby can obtain corresponding glucose concentration.

Specifically, a part (particularly, a sensing part) of the glucose monitoring probe 1 may be implanted on, for example, the body surface of a human body to be in contact with interstitial fluid in the body. In addition, another part of the glucose monitoring probe 1 is also connected with an electronic system 2 located outside the body surface. When the portable glucose monitor G is operated, the glucose monitoring probe 1 reacts with tissue fluid or blood in the body to generate a sensing signal (e.g., a current signal) and transmits the sensing signal to the electronic system 2 on the body surface, and the electronic system 2 processes the sensing signal to obtain the glucose concentration. Although fig. 1 shows a position where the glucose monitor probe 1 is disposed on the arm, the present embodiment is not limited thereto, and the glucose monitor probe 1 may be disposed on the abdomen, waist, leg, or the like, for example.

In the present embodiment, the glucose monitoring probe 1 may detect glucose in blood directly or in interstitial fluid. Further, the glucose concentration of interstitial fluid and the glucose concentration of blood are strongly correlated, and the glucose concentration of blood can be obtained from the glucose of interstitial fluid.

In the present embodiment, the glucose monitoring probe 1 may include a substrate S, and a working electrode 10, a reference electrode 20, and a counter electrode 30 (see fig. 2) provided on the substrate S. The glucose monitoring probe 1 further includes a contact 41 connected to the working electrode 10 via a lead, a contact 42 connected to the reference electrode 20 via a lead, and a contact 43 connected to the counter electrode 30 via a lead. Contact 41, contact 42, and contact 43 are all electrical contacts. In some examples, the glucose monitoring probe 1 may be connected with the electronic system 2 via

contacts

41, 42, and 43.

In some examples, the substrate S may be a flexible substrate. The flexible substrate may be substantially made of at least one of Polyethylene (PE), polypropylene (PP), Polyimide (PI), Polystyrene (PS), polyethylene terephthalate (PET), polyethylene naphthalate (PEN). In addition, in other examples, the flexible substrate may also be made of substantially metal foil, ultra-thin glass, a single-layer inorganic thin film, a multi-layer organic thin film, a multi-layer inorganic thin film, or the like.

In some examples, the substrate S may also be a non-flexible substrate. The non-flexible substrate may generally comprise a less conductive ceramic, alumina, silica, or the like. In this case, the glucose monitoring probe 1 with the non-flexible substrate may at the same time have a sharp point or a sharp edge, so that the glucose monitoring probe 1 can be implanted in a body surface (e.g., superficial skin layer, etc.) without the need for an auxiliary implantation device (not shown).

In the present embodiment, for convenience of explanation, the glucose monitoring probe 1 may be divided into a connection part 1a and an implantation part 1b (see fig. 3). The line A-A' in FIG. 3 generally shows the approximate location of the skin when the glucose monitoring probe 1 is implanted on the body surface of a tissue, with the attachment portion 1a located outside the body surface and the implanted portion 1b implanted in the body surface.

In addition, in some examples, both the connection portion 1a and the implantation portion 1b may include a flexible substrate, but the present embodiment is not limited thereto, and for example, only the implantation portion 1b may include a flexible substrate while the connection portion 1a includes a non-flexible substrate such as a rigid substrate.

In the present embodiment, the implanted portion 1b of the glucose monitoring probe 1 may be provided to an auxiliary puncture needle (not shown), and the implanted portion 1b may be separable from the puncture needle. Specifically, the piercing needle may be pierced into a tissue (e.g., a superficial skin layer), and then the piercing needle may be withdrawn and separated from the implanted portion 1b of the glucose monitoring probe 1, whereby the implanted portion 1b is left at the superficial skin layer and the electronic system 2 is brought into close contact with the skin surface, and the connection portion 1a (see fig. 3) of the glucose monitoring probe 1 is connected to the electronic system 2 and located at the skin surface. Here, the electronic system 2 may be adhered to the skin surface by an adhesive provided on the substrate S.

In some examples, the puncture needle serving as the auxiliary implanting function may have a notch, and the implanting portion 1b is placed in the notch of the puncture needle. Wherein the puncture needle can be made of stainless steel. In this case, the risk of use of the puncture needle can be reduced, and the puncture needle has sufficient hardness to facilitate skin puncture. Is beneficial to the use of patients. Additionally, in some examples, the needle may also be made of plastic, glass, or metal.

In this embodiment, an auxiliary implanting device (not shown), such as a needle assist device, may be used to pierce the piercing needle into the skin. Under the condition, the puncture depth can be configured in advance by using the needle assisting device, and the purposes of quick puncture, painless puncture and the like are realized by using the needle assisting device, so that the pain of a user is reduced. In addition, one-handed operation is also facilitated by the auxiliary implantation device. However, the present embodiment is not limited thereto, and for example, when the glucose monitoring probe 1 is a rigid substrate as described above, the glucose monitoring probe 1 may be implanted into the skin without the use of a puncture needle.

In the present embodiment, the depth of the glucose monitoring probe 1 implanted under the skin is determined according to the position to be penetrated, and when the fat layer is thick, the glucose monitoring probe is implanted deeper, for example, the abdomen of a human body, and the implantation depth is about 10mm to 15 mm. When the fat layer is thinner, the implantation depth is shallower, for example, at the arm, and the implantation depth is about 5mm to 10 mm.

Fig. 4 is a schematic configuration diagram showing the working electrode 10 of the glucose monitoring probe 1 according to the embodiment of the present invention. Fig. 5 is a schematic diagram showing that the carbon nanotube of the glucose monitoring probe 1 according to the embodiment of the present invention adsorbs glucosidase. Fig. 6 is a schematic diagram showing a glucose reaction between the glucose monitoring probe 1 according to the embodiment of the present invention and a tissue. Fig. 7 is a schematic structural view showing a semipermeable membrane of the working electrode 10 of the glucose monitoring probe 1 according to the embodiment of the present invention.

In the present embodiment, as described above, the implanted portion 1b of the glucose monitoring probe 1 includes the working electrode 10 (see fig. 2 and 3).

In this embodiment, the working electrode 10 may be provided with a basal layer 110, a sensing layer 120, a semi-permeable membrane 130, and a biocompatible membrane 140 (see fig. 4). In some examples, the substrate layer 110, the sensing layer 120, the semi-permeable membrane 130, and the biocompatible membrane 140 may be sequentially stacked.

In the present embodiment, the base layer 110 has conductivity. In some examples, the base layer 110 may be made of at least one selected from gold, glassy carbon, graphite, silver chloride, palladium, titanium, iridium. In this case, the base layer 110 can have good conductivity, and the electrochemical reaction of the base layer 110 can be suppressed, thereby improving the stability of the base layer 110.

In the present embodiment, in some examples, the base layer 110 may be disposed on the substrate S by a deposition or plating method. In some examples, the method of deposition may include physical vapor deposition, chemical vapor deposition, and the like. The plating method may include electroplating, electroless plating, vacuum plating, and the like. Additionally, in some examples, the base layer 110 may also be disposed on the substrate S by screen printing, extrusion, or electrolytic deposition, among others.

In this embodiment, the base layer 110 may be provided on a flexible substrate. Under the condition, the flexible substrate enables the whole product to be light and convenient, has strong shock resistance and reduces foreign body sensation after implantation. In other examples, the base layer 110 may also be disposed on a rigid substrate.

In this embodiment, the sensing layer 120 may be formed on the base layer 110 by coating a sensing layer reagent so as to be capable of chemically reacting with glucose. In some examples, the sensing layer reagents may include a metal polymer, a dextranase, carbon nanotubes 121, and a cross-linking agent. In this case, the sensing layer 120 contains the carbon nanotubes 121, and the catalytic action of the carbon nanotubes 121 on the glucose reaction reduces the working voltage required for the normal operation of the working electrode 10, thereby reducing the interference of the current generated by the electrochemical reaction of the electroactive substance under a high voltage to the working electrode 10.

Generally, carbon nanotubes are coaxial circular tubes having several to several tens of layers, which are mainly composed of carbon atoms arranged in a hexagonal pattern, and the layers are spaced apart from each other by a fixed distance of about 0.34nm, and the diameter is generally 2 to 20 nm.

In some examples, as shown in fig. 5, the carbon nanotube 121 may have a hollow cylindrical shape. Specifically, the carbon nanotube 121 may have a cylindrical or elliptical cylindrical shape. In addition, the carbon nanotube 121 has a strong adsorption capacity to organic substances due to its large surface area and surface hydrophobicity.

In the sensing layer 120, since the carbon nanotubes 121 can adsorb the glucolase and the metal polymer, the carbon nanotubes 121 can sufficiently contact and catalyze the reaction during the glucose reaction, thereby more effectively promoting the glucose reaction.

In this embodiment, the carbon nanotubes 121 may be added as a solvent to the sensing layer reagent. Thus, the sensing layer 120 including the carbon nanotubes 121 can be easily manufactured.

In some examples, the mass percentage of the carbon nanotubes 121 in the sensing layer reagent may be 5 to 10%. This can promote the reaction of the glucosidase more effectively, and reduce the waste of the carbon nanotubes 121.

In some examples, the sensing layer reagent may form the sensing layer 120 by at least one process of spin coating, dip-drawing, drop coating, or spray coating.

In the present embodiment, the sensing layer 120 may be a glucose oxidase sensing layer or a glucose dehydrogenase sensing layer.

Following, in conjunction with FIG. 6, with GO_X(FAD) As an example of glucose oxidase, the reaction occurring in the glucose sensing layer 120 will be described.

In the glucose sensing layer 130, when GO_X(FAD) when it encounters glucose in the tissue, the following reactions occur:

glucose + GOx (FAD) → gluconolactone + GOx (FADH)₂) … … reaction formula (I)

GOx(FADH₂)+O₂→GOx(FAD)+H₂O₂… … reaction formula (II)

As can be seen in the above reaction process, oxygen (O) is generated in the chemical reaction₂) Is consumed, O₂The reaction rate of the reaction of the formula (II) and the formula (I) is limited by O₂The reaction with tissue glucose may slow, resulting in failure of the glucose monitoring probe 1. In addition, in the above reaction process, there may be H in the reaction formula (II)₂O₂Product of (A), H₂O₂The aggregation may decrease the enzyme activity in the sensing layer 120 and may also cause the glucose monitoring probe 1 to fail. Therefore, by disposing the carbon nanotubes 121 between the base layer 110 and the sensing layer 120, H can be caused to exist by the action of the carbon nanotubes 121 as a catalyst₂O₂Decomposition reaction occurs, and the specific reaction is as follows:

H₂O₂→2H⁺+O₂+2e^-… … reaction formula (III)

The reaction with tissue glucose can be continued by the above reaction formulae (I) to (III). In addition, the carbon nanotube 121 is used to catalyze the hydrogen peroxide decomposition reaction, so that the reaction (III) can be accelerated and the voltage to be applied during the reaction can be reduced, which is beneficial to improving the sensitivity of the glucose monitoring probe 1, prolonging the service life of the glucose monitoring probe 1 and obtaining a low operating voltage. In other words, through the carbon nanotube 121, a high-sensitivity sensing signal of tissue glucose can be continuously obtained, the service time of the glucose monitoring probe 1 is prolonged, and meanwhile, the low working voltage is beneficial to improving the anti-interference performance.

In addition, in some examples, amino modifications may also be added to the carbon nanotubes 121 in the sensing layer reagent. In this case, the metal polymer and the carbon nanotube 121 can be tightly bound to each other by covalent bonds, and thus, the metal polymer and the carbon nanotube can be more stably bound to the glucosidase.

In other examples, graphene, porous titanium dioxide, or conductive organic salts may also be added to the sensing layer reagent. This can promote the reaction of the glucosidase more effectively.

In the present embodiment, the glucose monitoring probe 1 is implanted in the skin of a human body, and can continuously sample the glucose in the blood, convert the glucose into a corresponding current signal, and transmit the current signal to the electronic system 2 outside the body. In addition, sampling refers to a chemical reaction of glucose oxidase or dehydrogenase on the sensing layer 130 with glucose.

In this embodiment, the thickness of the sensing layer 120 may be about 0.1 μm to about 100 μm, preferably about 2 μm to about 10 μm, and in one example, the thickness of the sensing layer 120 may be about 10 μm. Under the condition, the thickness of the glucose oxidase or dehydrogenase is controlled within a certain degree, so that the problems that the adhesion force is reduced due to the fact that the glucose oxidase or dehydrogenase is too much, the materials fall off in vivo, the reaction is insufficient due to the fact that the glucose oxidase or dehydrogenase is too little, and normal glucose concentration information cannot be fed back are solved.

In this embodiment, as shown in fig. 4 and 7, the semi-permeable membrane 130 may be distributed on the sensing layer 120, that is, the semi-permeable membrane 130 may be disposed on the sensing layer 120.

In this embodiment, as shown in fig. 7, the semi-permeable membrane 130 may include a diffusion-controlling layer 131 and a tamper-resistant layer 132 laminated on the diffusion-controlling layer 131. In the semi-permeable membrane 130, the diffusion control layer 131 may control diffusion of glucose molecules, and the interference rejection layer 132 may block diffusion of non-glucose species. Therefore, the tissue fluid or blood component passing through the semipermeable membrane 130 can be reduced, and the interfering substance can be blocked outside the semipermeable membrane 130 by the interference-preventing layer 132. Common interferents may include uric acid, ascorbic acid, acetaminophen, etc., which are ubiquitous in the body.

In other examples, not limited to the example of fig. 7, in the semi-permeable membrane 130, the diffusion control layer 131 may also be laminated on the tamper resistant layer 132. In this case, too, it is possible to reduce the interference of impurities with the working electrode 10, improve the accuracy of the detection result, and prolong the service life of the glucose monitoring probe 1.

In this embodiment, the semi-permeable membrane 130 can control the passage rate of glucose molecules, i.e., the semi-permeable membrane 130 can limit the number of glucose molecules in interstitial fluid or blood that reach the sensing layer 120. Specifically, the diffusion-controlling layer 131 of the semi-permeable membrane 130 can effectively reduce the amount of glucose diffusing into the sensing layer 120 by a certain ratio.

In the present embodiment, the rate of reducing the amount of the entering matter by the diffusion control layer 131 is 10 to 100 times, preferably 30 to 80 times, for example, 50 times. In this case, the amount of glucose diffusing into the sensing layer 120 can be reduced, and a sufficient amount of glucose oxidase or dehydrogenase and other substances participating in the reaction can be ensured, and the glucose concentration becomes a factor for mainly limiting the magnitude of the electrode current, so that the magnitude of the current can correctly reflect the glucose concentration, and the linear range of the glucose monitoring probe 1 can be increased to a large extent.

In this embodiment, a biocompatible membrane 140 may be disposed on the semi-permeable membrane 130 (see fig. 4).

In some examples, the biocompatible membrane 140 may be made of a plant material. The plant material may be sodium alginate, tragacanth gum, pectin, acacia gum, xanthan gum, guar gum, agar, etc., or a derivative of a natural material. Among them, the natural material derivatives may include: starch derivatives, cellulose derivatives, and the like.

In other examples, the biocompatible membrane 140 may also be made of a synthetic material. The synthetic material may be a polyolefin: povidone, polyvinyl alcohol, polyisobutylene pressure-sensitive adhesive, ethylene-vinyl acetate copolymer, and the like; it may also be a polyacrylic: acrylic resin, carboxyvinyl-sucrose, carboxyvinyl-pentaerythritol copolymer, polyacrylate pressure-sensitive adhesive and the like; or polyoxyethylenes: polyesters such as polyoxyethylene fatty acid esters and polyoxyethylene-polyoxypropylene copolymers: polylactic acid, polyglycolide-lactide, polynearyl dinonyl sebacate, polycyanoalkyl amino ester, polyether polyurethane, and the like. Therefore, the immune response of the human body to the glucose monitoring probe 1 can be inhibited, and the service life of the glucose monitoring probe 1 is prolonged.

Additionally, in some examples, the semi-permeable membrane 130 may also be biocompatible. This can eliminate the use of the biocompatible film 140, thereby reducing the manufacturing cost.

In other examples, the permeability of the formed membrane to the analyte of interest may be adjusted by a modifying agent. For example, hydrophilic modifiers include: polyethylene glycol, hydroxyl or polyhydroxy modifiers. Thus, the biocompatibility of the film formed of the polymer may be increased, thereby replacing the biocompatible film 140.

In this embodiment, the biocompatible membrane 140 may cover the entire glucose monitoring probe 1. In some examples, the biocompatible membrane 140 may cover only the implanted portion 1b of the glucose monitoring probe 1 that is implanted in the body. This can reduce the use of raw materials.

In the present embodiment, the usage period of the glucose monitoring probe 1 may be 1 to 24 days, preferably 7 to 14 days. As described above, the semipermeable membrane 130 can restrict the entry of a part of glucose molecules and electroactive interfering substances, effectively extend the linear range of the glucose monitoring probe 1, and allow the sensing layer 120 to react with glucose oxidase or dehydrogenase more effectively, thereby stabilizing the life cycle of the glucose monitoring probe 1.

In addition, the glucose monitoring probe 1 can also be used in general tests, such as single test or short-time monitoring. For example, the monitoring time may be 1 hour to 24 hours or 24 hours to 36 hours.

In addition, the addition of the biocompatible membrane 140 enables the use period of the glucose monitoring probe 1 to be maintained from 1 day to 24 days, thereby enabling a user to conveniently select the glucose monitor G having the glucose monitoring probe 1 with different use periods according to different needs (e.g., price, etc.).

In the present embodiment, as described above, the glucose monitoring probe 1 may further include the reference electrode 20 and the counter electrode 30 (see fig. 2). Specifically, as shown in fig. 3, the implanted portion 1b of the glucose monitoring probe 1 may include a reference electrode 20 and a counter electrode 30.

In the present embodiment, the glucose monitoring probe 1 implanted in the skin can perform an oxidation-reduction reaction with glucose in interstitial fluid or blood by glucose oxidase or dehydrogenase in the working electrode 10, and form a circuit with the counter electrode 30 to generate a current signal.

In this embodiment, the reference electrode 20 may form a known and fixed potential difference with the interstitial fluid or blood. In this case, the potential difference between the working electrode 10 and the tissue fluid or blood can be measured by the potential difference formed between the reference electrode 20 and the working electrode 10, so that the voltage generated by the working electrode 10 can be accurately grasped. Therefore, the electronic system 2 can automatically adjust and maintain the voltage at the working electrode 10 to be stable according to the preset voltage value, so as to ensure that the measured current signal can accurately reflect the glucose concentration value.

In addition, in the present embodiment, the working electrode 10, the reference electrode 20, and the counter electrode 30 of the implanted portion 1b are arranged in a dispersed manner, but the embodiment of the present invention is not limited thereto, and may include a side-by-side (parallel) arrangement.

In addition, in the present embodiment, the glucose monitoring probe 1 is not limited to a planar probe, but may be a linear probe, a probe having stacked electrodes or layered electrodes, and a probe having coplanar electrodes in which electrodes are provided on the same plane.

In some examples, when the potential difference between the working electrode 10 and the interstitial fluid or blood does not fluctuate much, the reference electrode 20 may not be used.

In the present embodiment, the counter electrode 30 may be made of platinum, silver chloride, palladium, titanium, or iridium. Thereby, the electrochemical reaction at the working electrode 10 can be not affected with good conductivity. However, the present embodiment is not limited thereto, and in other examples, the counter electrode 30 may be made of at least one selected from gold, glassy carbon, graphite, silver chloride, palladium, titanium, or iridium. This can reduce the influence on the working electrode 10 while having good conductivity.

In addition, in some examples, the same material may be used for working electrode 10, counter electrode 30, and reference electrode 20.

In addition, in the present embodiment, the glucose monitoring probe 1 may include two, or three or more electrodes. For example, glucose monitoring probe 1 may include only two electrodes, working electrode 10 and counter electrode 30, and further, glucose monitoring probe 1 may include additional reference electrodes in addition to working electrode 10, reference electrode 20, and counter electrode 30. In this case, it is possible to obtain the potential difference of the working electrode 10 more accurately and grasp the voltage of the working electrode 10, thereby obtaining a more accurate current.

In the present embodiment, as described above, the connection portion 1a of the glucose monitoring probe 1 includes a plurality of contacts (feelers). The number of contacts is equal to the number of electrodes of the implanted portion 1b of the glucose monitoring probe 1. The contact is connected with the electrode of the implanted portion 1b through a lead (wire).

In the present embodiment, as shown in fig. 3, the number of electrodes of the implanted portion 1b of the glucose monitoring probe 1 is three. Accordingly, the connection portion 1a includes three contacts (contact tips), which are a contact 41, a contact 42, and a contact 43, respectively. However, the present embodiment is not limited to this, and for example, the number of electrodes of the implanted portion 1b may be two or more than four electrodes, and accordingly, the connection portion 1a may include two or more than four contacts (contacts).

In the present embodiment, the contact 41, the contact 42, and the contact 43 may each have a disk shape, and may be formed as a pad, for example. In addition, the contact 41, the contact 42, and the contact 43 may be formed as solder points. In other examples,

contacts

41, 42, and 43 may also be rectangular, oval, or other irregular shapes.

In the present embodiment, the current signal generated by the implanted portion 1b of the glucose monitoring probe 1 can be transmitted to the contact of the connection portion 1a through the base layer 110 and the transmission wire. That is, the implanted portion 1b of the glucose monitoring probe 1 is connected to the connection portion 1a, and the connection portion 1a is connected to the electronic system 2 via a plurality of contacts, so that the current signal obtained by the working electrode 10 is transmitted to the electronic system 2 through the contacts of the connection portion 1a for analysis. The electronic system 2 can analyze and process the current signal to obtain a glucose concentration signal.

Additionally, in some examples, the electronic system 2 may transmit to an external reading device via wireless communication, such as bluetooth, wifi, etc. A reading device (not shown) may receive the glucose concentration signal emitted by the electronic system 2 and display the glucose concentration value. Further, since the glucose monitoring probe 1 according to the present embodiment can realize continuous monitoring, it is possible to continuously monitor the glucose concentration value of the human body for a long period of time (for example, 1 to 24 days). Additionally, in some examples, the reading device may be a reader or a cell phone APP.

In addition, in this embodiment, the glucose monitoring probe 1 and the electronic system 2 may not require calibration during in vivo use. In addition, the glucose monitoring probe 1 and the electronic system 2 may be calibrated in advance at the time of factory shipment. Thus, the user's hassle of periodically calibrating the monitoring system by finger blood can be eliminated and the potential source of monitoring module reading errors during use reduced.

In the present embodiment, the electronic system 2 may be made of a flexible PCB and a flexible battery. Therefore, the skin can be attached to the skin, and the influence on the daily life of the user is reduced. In some examples, the outer shape of the electronic system 2 may be circular. In addition, in some examples, the electronic system 2 may also have a waterproof housing and a waterproof band-aid, thereby enabling use without affecting daily activities such as swimming or bathing.

In the present embodiment, the glucose monitoring probe 1 can acquire the glucose concentration in interstitial fluid or blood. However, the present embodiment is not limited to this, and for example, by changing the sensor layer 120 on the glucose monitoring probe 1, it is possible to acquire body fluid component data other than glucose, and body fluid components such as acetylcholine, amylase, bilirubin, cholesterol, chorionic gonadotropin, creatine kinase, creatine, creatinine, DNA, fructosamine, glucose, glutamine, growth hormone, ketone body, lactate, oxygen, peroxide, prostate-specific antigen, prothrombin, RNA, thyroid stimulating hormone, troponin, and the like.

In other examples, the concentration of a drug in a bodily fluid may also be monitored, such as antibiotics (e.g., gentamicin, vancomycin, and the like), digitoxin, digoxin, theophylline, and warfarin (warfarin), among others.

In this embodiment, first, the sensing layer 120 is formed on the underlayer 110 of the working electrode 10, then the semipermeable membrane 130 coating is formed on the sensing layer 120, and finally the biocompatible membrane 140 layer is formed on the semipermeable membrane 130 coating. Therefore, the service life of the glucose monitoring probe 1 is prolonged, the interference of other factors is reduced, and the reaction speed of the glucose monitoring probe 1 to glucose is increased.

Hereinafter, a method of manufacturing the working electrode 10 of the glucose monitoring probe 1 will be described in detail with reference to the drawings.

Fig. 8 is a flowchart illustrating a method for manufacturing the working electrode 10 of the glucose monitoring probe 1 according to the embodiment of the present invention. Fig. 9 is a flowchart illustrating a method for manufacturing the semipermeable membrane 130 of the working electrode 10 of the glucose monitoring probe 1 according to the embodiment of the present invention.

In the present embodiment, the method for manufacturing the working electrode 10 of the glucose monitoring probe 1 may include (see fig. 8): preparing a flexible substrate and forming a base layer 110 on the flexible substrate (step S110); preparing a sensing layer 120 reagent including a metal polymer, a glucolase, carbon nanotubes 121, and a cross-linking agent (step S120); coating a sensing layer reagent on the base layer 110 and forming a sensing layer 120 (step S130); forming a semi-permeable membrane 130 for controlling a passing rate of glucose molecules on the sensing layer 120 (step S140); and a biocompatible membrane 140 is formed on the semi-permeable membrane 130 (step S150). In this case, the carbon nanotubes 121 are contained in the sensing layer 120. Therefore, the working voltage of the working electrode 10 is reduced, the interference of other factors is reduced, the reaction sensitivity of the probe to the glucose is improved, the linear range of the response of the glucose monitoring probe 1 to the glucose can be enlarged, and the service life of the probe is prolonged.

As described above, in step S110, a flexible substrate is prepared, and the base layer 110 is formed on the flexible substrate. In some examples, the base layer 110 may also be fabricated by one or more of electroplating, evaporation, printing, or extrusion, among others.

In the present embodiment, in step S130, the sensing layer 120 may be a glucose oxidase sensing layer or a glucose dehydrogenase sensing layer.

In the manufacturing method according to the present embodiment, as shown in fig. 9, the step S140 may include forming the interference suppression layer 132 on the sensor layer 120 (step S141), and further forming the diffusion control layer 131 on the interference suppression layer (step S142). Thus, the tissue fluid or blood component passing through the semipermeable membrane 130 can be reduced by the interference prevention layer 132, and the interfering substance can be blocked outside the semipermeable membrane 130 by the diffusion control layer 131.

In some examples, in step S140, the order of step S141 and step S142 may be interchanged. That is, the diffusion-controlling layer 131 may be first formed on the glucose oxidase or dehydrogenase layer (step S142), and then the tamper-resistant layer 132 may be formed on the diffusion-controlling layer 131 (step S141). Therefore, the interference of impurities on the working electrode 10 can be reduced, the inaccurate detection result can be prevented, and the service life of the glucose monitoring probe 1 can be prolonged.

While the present invention has been described in detail in connection with the drawings and the examples, it is to be understood that the above description is not intended to limit the present invention in any way. The present invention may be modified and varied as necessary by those skilled in the art without departing from the true spirit and scope of the invention, and all such modifications and variations are intended to be included within the scope of the invention.

Claims

1. A working electrode of a glucose monitoring probe is characterized in that,

the disclosed device is provided with:

a base layer formed on a flexible substrate;

a sensing layer formed on the base layer by coating a sensing layer reagent, the sensing layer reagent being capable of chemically reacting with glucose, the sensing layer reagent including a metal polymer, a glucosidase, a carbon nanotube and a cross-linking agent, the carbon nanotube having a hollow columnar shape, the carbon nanotube adsorbing the metal polymer and the glucosidase, the sensing layer reagent including an amino group modification added to the carbon nanotube, the metal polymer being covalently bonded to the carbon nanotube;

a semi-permeable membrane formed on the sensing layer, controlling the passage rate of glucose molecules; and

a biocompatible membrane formed on the semi-permeable membrane.

2. The working electrode of claim 1,

the semi-permeable membrane includes a diffusion controlling layer that controls diffusion of glucose molecules.

3. The working electrode of claim 1,

the semi-permeable membrane includes an anti-interference layer that blocks non-glucose species.

4. The working electrode of claim 1,

the thickness of the sensing layer is 0.1 μm to 100 μm.

5. The working electrode of claim 1,

the service life of the probe is 1 to 24 days.