阅读说明：本技术 生物传感器探针用保护膜材料 (Protective film material for biosensor probe ) 是由 远藤太志 池田纯子 于 2019-01-28 设计创作，主要内容包括：本发明使用一种膜结构体作为在埋入型生物传感器的探针中有用的膜结构体,其具备包含检测体响应性酶的检测层、以及在上述检测层上形成的保护膜,上述保护膜包含交联剂和聚(苯乙烯-无规-4-乙烯基吡啶-无规-甲基丙烯酸丙二醇酯)、以及聚(4-乙烯基吡啶)-嵌段-聚(甲基丙烯酸C<Sub>1-15</Sub>烷基酯)或者聚(4-乙烯基吡啶-无规-甲基丙烯酸2-羟基乙酯)。(The present invention uses a membrane structure comprising a detection layer containing a detection-responsive enzyme, and a protective film formed on the detection layer, the protective film comprising a crosslinking agent, poly (styrene-random-4-vinylpyridine-random-propylene glycol methacrylate), and poly (4-vinylpyridine) -block-poly (methacrylic acid C-methyl acrylate), as a membrane structure useful for a probe of an embedded biosensor 1‑15 Alkyl ester) or poly (4-vinylpyridine-random-2-hydroxyethyl methacrylate).)

1. A membrane structure comprising a detection layer containing at least a detection-responsive enzyme and a redox mediator, and a protective film formed on the detection layer, the protective film comprising:

poly (4-vinylpyridine) -block-poly (methacrylic acid C) represented by formula (1)_1-15Alkyl esters); or

Comprising poly (4-vinylpyridine) -block-poly (methacrylic acid C) represented by the formula (1)_1-15Alkyl ester) with poly (4-vinylpyridine-random-2-hydroxyethyl methacrylate) of formula (2),

in the formula (1), R represents alkyl with 1-15 carbon atoms, p and q respectively represent 2 monomer units, namely 4-vinylpyridine and methacrylic acid C_1-15Alkyl ester repeating units, w represents a number average molecular weight,

in formula (2), s and t represent the mole percentages of 2 monomer units, i.e., 4-vinylpyridine and 2-hydroxyethyl methacrylate, respectively, and s + t is 100, and w represents the number average molecular weight.

2. The membrane structure of claim 1, wherein the protective membrane further comprises poly (2-methoxyethyl acrylate).

3. A probe for a biosensor, comprising an insulating substrate, conductive thin films formed on both surfaces of the insulating substrate, a working electrode and a reference electrode formed on the conductive thin film on the front surface side of the insulating substrate, a counter electrode formed on the conductive thin film on the back surface side of the insulating substrate, a detection layer formed on the working electrode, and a protective film covering the working electrode, the reference electrode, the counter electrode, and the detection layer, wherein the detection layer contains a sample-responsive enzyme and a redox mediator, and the protective film contains:

a poly represented by the formula (1)(4-vinylpyridine) -block-poly (methacrylic acid C)_1-15Alkyl esters); or

Comprising poly (4-vinylpyridine) -block-poly (methacrylic acid C) represented by the formula (1)_1-15Alkyl ester) with poly (4-vinylpyridine-random-2-hydroxyethyl methacrylate) of formula (2),

in the formula (1), R represents alkyl with 1-15 carbon atoms, p and q respectively represent 2 monomer units, namely 4-vinylpyridine and methacrylic acid C _1-15Alkyl ester repeating units, w represents a number average molecular weight,

in formula (2), s and t represent the mole percentages of 2 monomer units, i.e., 4-vinylpyridine and 2-hydroxyethyl methacrylate, respectively, and s + t is 100, and w represents the number average molecular weight.

Technical Field

The present disclosure relates to a membrane material for protecting a probe constituting a biosensor. More specifically, a polymer material for a protective film capable of preventing the outflow of an enzyme or a mediator constituting a biosensor probe inserted into the body is provided.

Background

A biosensor is a system for measuring a substance by utilizing or simulating the molecular recognition ability of a living body, and is, for example, a measuring apparatus in which one of combinations of an enzyme-substrate, an antigen-antibody, a hormone-receptor, and the like is used as a detection body (a substance to be measured), the other is used as a receptor, a chemical change caused by a molecular recognition reaction between the detection body and the receptor is converted into an electric signal by a transducer, and the amount of the detection body is measured based on the intensity of the obtained electric signal.

The biomolecule used in the biosensor includes genes, sugar chains, lipids, peptides, cells, tissues, and the like in addition to the above. Among them, biosensors using enzymes have been developed most rapidly, and a representative example thereof is a Glucose sensor using Glucose oxidase (GOx).

An electrochemical glucose sensor used for self-blood glucose measurement is generally configured such that a cap is disposed on an insulating substrate having electrodes formed on the surface thereof, with a spacer interposed therebetween. The electrode is provided with a reagent containing a sample-responsive enzyme, a redox mediator (electron conductor), and the like, and this portion serves as an analysis section. One end of a channel for introducing blood communicates with the analysis section, and the other end of the channel opens to the outside, and is referred to as a blood supply port. The blood glucose level using such a sensor is measured, for example, as follows. That is, first, the sensor is mounted on a dedicated measuring device (measuring instrument). Then, a fingertip or the like is pricked with a lancet to bleed, and the blood supply port of the sensor is brought into contact with the fingertip or the fingertip. The blood is drawn into the channel of the sensor by capillary action, and is introduced into the analysis section through the channel, where it comes into contact with the reagent. Then, the sample-responsive enzyme E (e.g., GOx, GDH) oxidizes glucose by a specific reaction with glucose in blood. The redox mediator M accepts electrons generated by oxidation. The redox mediator M that has received electrons and has been reduced is electrochemically oxidized by an electrode. The glucose concentration in blood, i.e., the blood glucose level, can be easily detected based on the magnitude of the current value, the charge amount, and the like obtained by oxidation of the reducing redox mediator M.

Such an electrochemical blood glucose sensor plays an important role in blood glucose management in diabetes treatment, and a diabetic patient can appropriately administer insulin or control diet based on the blood glucose level. However, the blood glucose level must be measured several times a day, and each blood collection can increase the pain of the patient and make it difficult to maintain the Quality of Life (Quality of Life; QOL).

Embedded amperometric glucose sensors have been developed. The main body 10 of the embedded amperometric glucose sensor 1 is attached to the living body 2, and the blood glucose level is continuously measured by inserting the probe portion 11 into the living body (fig. 1 and 2). This makes it possible to measure the blood glucose level for a long period of time without requiring each blood collection.

"telemedicine notification in 9 years (healthcare issue No. 1075 health policy bureau of pachyson department, 24 days in 12 months in 9 years)" is performed by the japan university labour, and shows the basic ideas of telemedicine and the matters to be noticed in relation to the japanese medical law, article 20, and the like. Then, in view of the situation of development and popularization of information communication equipment, a business contact was made with the public prefecture of each prefecture on a medical treatment (so-called "telemedicine") using information communication equipment on 8/10/2015. According to the notification in 2015, the remote diagnosis is in fact prohibited, and in 2016, a remote diagnosis tool using an information communication device 3 (smartphone) and dedicated application software for wireless data communication with the biosensor 1 is coming into the market (fig. 3). Further, on 14 th 7 th 2017, the remote diagnosis and treatment operations are notified again with a well-known clear idea (japanese medical administration 0714 No. 4). According to the report in 2015, even for a remote diagnosis combining information communication devices such as video phones, e-mails, social network services, and the like, if useful information on the physical and mental conditions of a patient is available to the extent that the information can replace direct current diagnosis, the remote diagnosis does not directly conflict with japanese medical law article 20 and the like, as long as the person concerned can be confirmed as a doctor and the patient themselves. Telemedicine using an information communication device will be further developed due to the 2017 notice. Therefore, the demand for embedded sensors is expected to increase.

Patent document 1 discloses an electrochemical sensor control device that is attached to a patient and inserted into the skin using a wireless transmitter, and describes a technique of transmitting collected data on the amount of a detected object to a display device using a wireless transmitter. Patent document 1 also discloses a film containing a heterocyclic nitrogen group such as vinylpyridine, which is mounted on such an electrochemical sensor. These membranes limit diffusion of the detection body in the electrochemical sensor to the working electrode. In a glucose sensor having no membrane, the flow rate of glucose to the detection layer increases linearly together with the glucose concentration, and when the glucose consumption is limited in the detection layer, the measurement signal is saturated and does not linearly proportion to the flow rate or concentration of glucose, while the output signal measured linearly proportion to the flow rate of glucose in the course of the consumption of all the glucose that has reached the detection layer. Therefore, patent document 1 adopts a technique of forming a diffusion limiting film containing a heterocyclic nitrogen group such as polyvinylpyridine on the detection layer to reduce the flow rate of glucose to the detection layer, thereby preventing saturation of the sensor.

Patent document 2 discloses a diffusion barrier comprising a single block copolymer having at least one hydrophilic block and at least one hydrophobic block, which is a member for controlling diffusion of an analyte from the outside of an electrode system to an enzyme molecule, as in patent document 1. In addition, such enzyme molecules are immobilized to an electrode to form an enzyme layer. In the production of such an enzyme layer, as disclosed in patent document 3, for example, the enzyme can be immobilized on the working electrode by adsorption and capture, and further firmly immobilized by crosslinking with glutaraldehyde or the like.

Disclosure of Invention

Problems to be solved by the invention

Since the probe of the embedded sensor is inserted into the body for a long time, the chance of elution of the detection-responsive enzyme and the redox mediator, which are components, increases. If the sample-responsive enzyme or the redox mediator flows out of the sensor, not only the sensitivity of the sensor deteriorates, but also the living body is damaged. In addition, if the sample-responsive enzyme or the redox mediator is eluted to the outside, the durability of the sensor is also reduced. Therefore, measures for preventing the outflow of the sample-responsive enzyme and the redox mediator are very important.

If it is desired to immobilize both a detection-responsive enzyme and a redox mediator constituting a probe of an embedded biosensor to prevent elution, the combination of an enzyme and a mediator polymer that can be used, and the structure of the sensor, are limited. Therefore, it is desired to develop a membrane that is formed on a detection layer containing an enzyme and/or a redox mediator and can prevent the enzyme and the redox mediator from flowing out to the outside. In addition, such a membrane cannot prevent a specimen such as glucose from entering the inside. Accordingly, an object of the present disclosure is to provide a protective film that prevents an enzyme and a redox mediator from flowing out to the outside without inhibiting the entry of a detection object into the inside, in order to be applied to a probe of an embedded biosensor.

Means for solving the problems

The present disclosure provides a membrane structure useful as a probe for a biosensor, comprising a detection layer containing at least a detection-responsive enzyme and a redox mediator, and a protective film formed on the detection layer, the protective film comprising: poly (4-vinylpyridine) -block-poly (methacrylic acid C) represented by formula (1)_1-15Alkyl esters); or poly (4-vinylpyridine) -block-poly (methacrylic acid C) represented by the formula (1)_1-15Alkyl ester) with poly (4-vinylpyridine) of the formula (2)-random-2-hydroxyethyl methacrylate). In the formula, the diagonal lines between the monomers do not indicate that the 3 kinds of monomer units are in the order described in the formula, but indicate that the monomer units are bonded irregularly except for unevenness due to reactivity between the monomer units.

[ chemical formula 1]

[ wherein R represents an alkyl group having 1 to 15 carbon atoms, and p and q each represent 2 monomer units, i.e., 4-vinylpyridine and methacrylic acid C_1-15Alkyl ester repeating units, w represents a number average molecular weight.]

[ chemical formula 2]

In the formula, s and t represent the mole percentages of 2 monomer units, i.e., 4-vinylpyridine and 2-hydroxyethyl methacrylate, respectively, s + t is 100, and w represents the number average molecular weight. ]

The polymer represented by the above formula (1) is a copolymer of poly (4-vinylpyridine) and poly (methacrylic acid C)_1-15Alkyl ester), repeating units p of 4-vinylpyridine constituting poly (4-vinylpyridine), and poly (methacrylic acid C)_1-15Alkyl ester) of methacrylic acid alkyl ester each having a number average molecular weight of 50 to 200X 10 in each block constituting the above polymer³Preferably 60 to 100X 10³The method (2) is selected.

Among the polymers represented by the above formula (1), poly (methacrylic acid C)_1-15Alkyl ester) C_1-15The alkyl group represents an alkyl group having 1 to 15 carbon atoms, and examples thereof include a methyl group, an ethyl group, a propyl group, a butyl group, a pentyl group, a hexyl group, a heptyl group, an octyl group, a nonyl group, a decyl group, an undecyl group, a dodecyl group, a tridecyl group, a tetradecyl group, a pentadecyl group, and isomers thereof, and preferably C_3-6An alkyl group.

Polymerization represented by the above formula (2)The composition is advantageous for improving biocompatibility, and is a random copolymer comprising 4-vinylpyridine and 2-hydroxyethyl methacrylate as monomer units, wherein the molar percentage s of 4-vinylpyridine is 40 to 80, preferably 60 to 70, and the molar percentage t of 2-hydroxyethyl methacrylate is 20 to 60, preferably 30 to 40, and s and t may not be integers as long as the total of s and t is 100. The number average molecular weight of the polymer is 20 to 500X 10 ³Preferably 60 to 300X 10³。

The polymer may be crosslinked with a crosslinking agent such as polyethylene glycol diglycidyl ether (PEGDGE).

The protective film may further contain, for example, poly (2-methoxyethyl acrylate) as an additive. Thus, the biocompatibility of the protective film is improved.

Effects of the invention

When the protective film is formed using the polymer for protective film of the present disclosure on the detection layer containing the enzyme and the mediator constituting the probe of the embedded biosensor, the enzyme and the mediator contained in the detection layer can be prevented from flowing out without inhibiting the entry of a detection substance such as glucose into the interior.

Drawings

Fig. 1 is a schematic view showing a state in which an embedded biosensor is attached to a living body (human body).

Fig. 2 is a sectional view showing an embedded biosensor attached to a living body (human body).

Fig. 3 is a schematic diagram of an embedded biosensor that wirelessly communicates measurement data with a smartphone.

FIG. 4 shows a process for producing a probe of an embedded biosensor, which is one specific example of the present disclosure.

FIG. 5 shows a process for producing a probe of an embedded biosensor, which is one specific example of the present disclosure.

FIG. 6 shows a process for producing a probe of an embedded biosensor, which is one specific example of the present disclosure.

Fig. 7 is a plan view of the probe surface side of an embedded biosensor, which is one specific example of the present disclosure.

FIG. 8 is a cross-sectional view at the cut line A-A' of FIG. 7.

Fig. 9 is a sectional view at the B-B' cut line of fig. 8.

FIG. 10 is a cross-sectional view at the cut line C-C' of FIG. 8.

Fig. 11 is a graph showing glucose response characteristics of a probe using the copolymer or copolymer mixture of the present disclosure for a protective film.

Fig. 12 is a graph showing durability of a probe using the copolymer or copolymer mixture of the present disclosure for a protective film.

FIG. 13 is a graph showing glucose response characteristics of a probe using a polymer of a comparative example for a protective film and a probe using a conventional copolymer for a protective film.

Fig. 14 is a graph showing durability of a probe using the polymer of the comparative example for the protective film and a probe using the conventional copolymer for the protective film.

FIG. 15 is a graph showing glucose response characteristics of a probe using the polymer of the reference example as a protective film and a probe using a conventional copolymer as a protective film.

Fig. 16 is a graph showing durability of a probe using the polymer of the reference example for the protective film and a probe using the conventional copolymer for the protective film.

Detailed Description

1. Method for manufacturing probe of embedded biosensor

A method for producing probe 11 of embedded biosensor 1 to which a specific example of the membrane structure of the present disclosure is applied will be described. The structure and the manufacturing method shown below are specific examples of the present disclosure, and are not limited to the following configurations as long as they can be used as probes.

(1) Preparation of insulating substrate

The embedded biosensor 1 includes a body 10 and a probe 11, and the probe 11 has a key shape including a sensing portion inserted into a living body and a terminal portion for electrical connection with an internal circuit of the biosensor body 10. The sensing part is formed thin in such a manner as to be inserted into the body, and the terminal part is sized in such a manner as to be inserted into the biosensor body 10 to form an electrical connection. Therefore, first, a key-shaped insulating substrate 111 is prepared (fig. 4 a). The upper stage shows a plan view from the front side, and the lower stage shows a plan view from the back side (the same applies hereinafter). The insulating substrate 111 is not particularly limited as long as it is a material and thickness that can be used as a probe inserted into a living body, and for example, polyethylene terephthalate (PET) having a thickness of about 200 μm can be used.

(2) Formation of conductive thin film

A conductive metal material such as carbon or a metal selected from gold, silver, platinum, or palladium is deposited on both surfaces of the insulating substrate 111 by sputtering, vapor deposition, or ion plating, thereby forming conductive thin films 112 (fig. 4 b). The thickness of the conductive thin film is preferably 10nm to several hundred nm.

(3) Formation of electrode leads

The conductive thin film 112 formed on the front surface side of the insulating substrate 111 is provided with a groove 113 formed by laser drawing to a depth reaching the front surface of the insulating substrate 111, thereby separating and electrically insulating the working electrode lead 112a and the reference electrode lead 112b (fig. 5 c).

(4) Formation of insulating resist film

An insulating resist film 116a having an opening is formed by sputtering, screen printing or the like on the front surface side of the insulating substrate 111 except for the region used as the working electrode terminal 114a and the reference electrode terminal 115a for electrically connecting the working electrode 114 and the reference electrode 115 and the main body 10, and an insulating resist film 116b having an opening is formed by sputtering, screen printing or the like on the back surface side of the insulating substrate 111 except for the region used as the counter electrode terminal 117a for electrically connecting the counter electrode 117 and the main body 10 (fig. 5 d). The insulating resist film preferably has a thickness of 5 to 40 μm.

(5) Formation of reference electrode

The reference electrode 115 is formed by depositing Ag/AgCl through a screen printing method or an ink jet method in the opening for the reference electrode of the resist film 116a formed on the front surface side of the insulating substrate 111 (fig. Se). The reference electrode preferably has a thickness of 5 to 40 μm.

(6) Formation of detection layer

A detection layer 118 (fig. 6f) containing conductive particles, a sample-responsive enzyme, and a redox mediator is formed by applying and drying a suspension of conductive particles such as carbon particles, an aqueous solution of a sample-responsive enzyme, and an aqueous solution of a redox mediator on the working electrode 114. In the present disclosure, the "detection body-responsive enzyme" refers to a biochemical substance capable of specifically catalyzing oxidation or reduction of a detection body. Any biochemical substance may be used as long as it can be used for the detection purpose of the biosensor. For example, in the case of using Glucose as a detection reagent, suitable detection-responsive enzymes include Glucose oxidase (GOx), Glucose Dehydrogenase (GDH), and the like. The "redox mediator" refers to a redox substance that mediates electron conduction, and serves to conduct electrons generated by a redox reaction of a sample (analyte) in the biosensor. For example, phenazine derivatives and the like are included, but not limited thereto, and any redox substance may be used as long as it can be used for the detection purpose of the biosensor. The detection layer preferably has a thickness of 5 to 80 μm.

(7) Formation of protective film

The sensing part is immersed in a solution containing a polymer for a protective film to form a protective film 119 on both sides, side surfaces and top of the sensing part (fig. 6 g). The protective film 119 is formed to have a length of not less than the length of insertion into the living body, so as to cover at least the working electrode 114, the reference electrode 115, the counter electrode 117, and the detection layer 118, without covering the working electrode terminal 114a, the reference electrode terminal 115a, and the counter electrode terminal 117 a. The preferable thickness of the protective film is 5 to 200 μm.

2. Internal structure of probe of embedded biosensor

Further, the internal structure of the probe of the embedded biosensor to which the membrane structure of the present disclosure is applied will be described.

The cross-sectional view at the cut line A-A' of FIG. 7 is shown in FIG. 8. Conductive thin films 112 are formed on both sides of the insulating substrate 111. The front side conductive film 112 is separated into 2 leads of a working electrode lead 112a and a reference electrode lead 112b by a groove 113 and is electrically insulated. A part of the working electrode lead 112a functions as a working electrode 114, and a detection layer 118 is formed on the working electrode 114. A reference electrode 115 is formed in the opening of the insulating resist film 116a, and is electrically connected to the reference electrode lead 112 b. The back side conductive film 112 serves as a counter electrode lead 112c, and a part thereof functions as a counter electrode 117.

The cross-sectional view at the B-B' cut line of FIG. 8 is shown in FIG. 9. A working electrode 114, a detection layer 118, and a counter electrode 117 are formed on the front surface side and the back surface side of the insulating substrate 111, respectively. Further, the entire periphery of the sensing portion is covered with the protective film 119 of the present disclosure.

The cross-sectional view at the C-C' cut plane of fig. 8 is shown in fig. 10. A working electrode lead 112a and a reference electrode lead 112b electrically separated by a groove 113 are formed on the front surface side of the insulating substrate 111, and an insulating resist film 116a is formed thereon. A reference electrode 115 is formed in the opening of the insulating resist film 116 a. A counter electrode lead 112c is formed on the back surface side of the substrate 111, and an insulating resist film 116b is formed thereon. Further, the entire periphery of the sensing portion is covered with the protective film 119 of the present disclosure.