JP4435703B2 - Biosensor - Google Patents

Description

  The present invention relates to a biosensor and a method for analyzing an interaction between biomolecules using the biosensor. In particular, the present invention relates to a biosensor for use in a surface plasmon resonance biosensor and a method for analyzing an interaction between biomolecules using the biosensor.

  Currently, many measurements using intermolecular interactions such as immune reactions are performed in clinical examinations, etc., but conventional methods require complicated operations and labeling substances, so measurement without the need for labeling substances Several techniques that can detect a change in the amount of a substance bound with high sensitivity are used. For example, surface plasmon resonance (SPR) measurement technology, quartz crystal microbalance (QCM) measurement technology, and measurement technology using functionalized surfaces from gold colloidal particles to ultrafine particles. SPR measurement technology detects adsorption and desorption near the surface by measuring the refractive index change in the vicinity of the organic functional film in contact with the metal film of the chip by measuring the peak shift of the reflected light wavelength or the change in the amount of reflected light at a fixed wavelength. It is a method to do. The QCM measurement technique is a technique that can detect the adsorption / desorption mass at the ng level from the change in the oscillation frequency of the oscillator due to the adsorption / desorption of a substance on the gold electrode (device) of the crystal oscillator. In addition, by functionalizing the surface of gold ultrafine particles (nm level), immobilizing a physiologically active substance on the surface, and performing a specific recognition reaction between the physiologically active substances, it is possible to obtain a living body from the sedimentation and arrangement of gold fine particles. Related substances can be detected.

  In any of the above techniques, the surface on which the physiologically active substance is immobilized is important. Hereinafter, the surface plasmon resonance (SPR) most used in this technical field will be described as an example.

  A commonly used measurement chip is composed of a transparent substrate (eg, glass), a deposited metal film, and a thin film having a functional group capable of immobilizing a physiologically active substance thereon, and the metal surface is interposed through the functional group. Immobilize physiologically active substances. The interaction between biomolecules is analyzed by measuring a specific binding reaction between the physiologically active substance and the analyte substance.

  As a detection surface having a functional group capable of immobilizing a physiologically active substance, for example, Patent Document 1 discloses a method for producing a hydrogel in detail. Specifically, a barrier layer is formed by bonding a 16-mercaptohexadecanol layer to a gold film. On this gold film, the hydroxyl group of the barrier layer is epoxy activated by treating with epichlorohydrin. In the next step, dextran is attached to the barrier layer via an ether linkage. Next, a carboxymethyl group is introduced by reacting the dextran matrix with bromoacetic acid.

As a technique for immobilizing a physiologically active substance having an amino group (for example, a protein or amino acid) on the surface of a carboxymethyl-modified dextran produced based on this method, the following technique is disclosed. That is, for example, N-hydroxysuccinimide (NHS) and N- (3-dimethylaminopropyl) -N'-ethylcarbodiimide (EDC) hydrochloric acid are used so that a part of the carboxyl group in the carboxymethyl-modified dextran generates a reactive ester function. Denatured by treatment with aqueous solution. Residual charges, i.e. unreacted carboxyl groups, will contribute to the concentration of the bioactive substance to the detection surface. By bringing an aqueous solution of a physiologically active substance (protein or amino acid) containing an amino group into contact with such a detection surface, the physiologically active substance containing an amino group can be covalently bound to the dextran matrix.

The hydrogel produced by the method described above exhibits excellent performance as a detection surface of a biosensor because a physiologically active substance containing an amino group can be immobilized three-dimensionally. However, the hydrogel production method by the above-described method is complicated, has a long production time, and requires the use of a compound such as epichlorohydrin or bromoacetic acid.

Japanese Patent No. 2815120

  The present invention has been made to solve the above-described problems of the prior art. That is, an object of the present invention is to provide a biosensor capable of easily producing a hydrogel capable of immobilizing a physiologically active substance using a safe raw material and a method for producing the same.

  As a result of intensive studies to solve the above problems, the present inventors can react a polymer hardener developed for the production of a silver halide photographic light-sensitive material with a hydroxyl group or an amino group of a physiologically active substance. As a hydrophilic polymer having a reactive functional group, a hydrogel capable of immobilizing a physiologically active substance can be easily produced by applying it as a hydrogel for a detection surface of a biosensor, and the present invention is completed. It came to.

  That is, according to the present invention, a hydrophilic polymer having a metal layer on the surface and having a reactive functional group capable of reacting with the hydroxyl group or amino group of a physiologically active substance directly or via an intermediate layer. A biosensor comprising a substrate to which is bound is provided.

Preferably, the reactive functional group of the hydrophilic polymer is a vinyl sulfone group or a precursor thereof.
Preferably, the reactive functional group of the hydrophilic polymer is a dichlorotriazine group.
Preferably, the biosensor of the present invention forms a dense layer on the metal surface using a disulfide that is an alkanethiol having a reactive group at the terminal or an oxidized form thereof, and then has a reactive group at the terminal of the alkanethiol; It can be obtained by reacting a hydrophilic polymer having a reactive functional group capable of reacting with a hydroxyl group or amino group of a physiologically active substance.
Preferably, the carboxylic acid is introduced by reacting the reactive functional group of the hydrophilic polymer with an amino acid.

Preferably, the film thickness of the intermediate layer is not less than 0.1 nm and not more than 500 nm.
Preferably, the metal is any of gold, silver, copper, platinum or aluminum.
Preferably, the biosensor of the present invention is used for non-electrochemical detection, more preferably for surface plasmon resonance analysis.

  According to another aspect of the present invention, a hydrophilic polymer having a reactive functional group capable of reacting with a hydroxyl group or an amino group of a physiologically active substance directly or via an intermediate layer on the surface of a substrate having a metal layer on the surface. There is provided a method for producing the biosensor of the present invention as described above, which comprises a step of chemically binding.

  According to still another aspect of the present invention, a physiologically active substance is covalently bonded to a reactive functional group of a carboxylic acid introduced by reacting a hydrophilic polymer or a reactive functional group with an amino acid. The biosensor of the present invention is provided.

  According to still another aspect of the present invention, the biosensor includes a step of bringing the biosensor of the present invention into contact with the physiologically active substance and binding the physiologically active substance to the surface of the biosensor. A method of immobilization is provided.

According to still another aspect of the present invention, a substance that interacts with a physiologically active substance, comprising the step of bringing the biosensor of the present invention in which the physiologically active substance is covalently bonded to the surface with the test substance. A method of detecting or measuring is provided.
Preferably, the substance that interacts with the physiologically active substance is detected or measured by a non-electrochemical method, and more preferably, the substance that interacts with the physiologically active substance is detected or measured by surface plasmon resonance analysis.

  ADVANTAGE OF THE INVENTION According to this invention, it became possible to provide the biosensor which can manufacture a hydrogel which can fix | immobilize a physiologically active substance simply using a safe raw material, and its manufacturing method.

Embodiments of the present invention will be described below.
The biosensor of the present invention has a metal layer on the surface, and a hydrophilic polymer having a reactive functional group capable of reacting with a hydroxyl group or an amino group of a physiologically active substance directly or via an intermediate layer. It consists of the board | substrate which has couple | bonded.

  As the hydrophilic polymer having a reactive functional group capable of reacting with the hydroxyl group or amino group of the physiologically active substance used in the present invention, a polymer hardener for silver halide photography can be used. Hereinafter, the polymer hardener that can be used in the present invention will be described. The polymer hardener is a polymer compound having a plurality of reactive functional groups in the molecule that bind and react with a hydrophilic colloid such as gelatin. JP-A-56-66841, British Patent 1, No. 322,971, US Pat. No. 3,671,256, JP-A-7-64226, JP-A-7-140596, JP-A-10-111545, JP-A-2000-62629, JP Patent Literature such as 2004-20919, and The Theory of the Photographic Process by James (James, The Theory of the Photographic Process), 4th edition, page 84 (1977, Macmillan), Campbell Other authors: Polymeric Amine and Ammonium Salts ; Polymeric Amine and Ammonium Salts), pp 321-332 (1979, are described in textbooks par Gammon Press, Inc.) and the like.

The polymer hardener used in the present invention is a polymer compound having a reactive functional group capable of binding to a functional group on the biosensor surface, and is preferably represented by the following formulas (1) to (9). It is a polymer compound having a reactive functional group.
Equation _{(1): -SO 2 CH =} CH 2
Equation _{(2): -SO 2 CH 2} CH 2 X
In the formula (2), X represents a group (for example, —Cl, —OSO ₂ CH, etc.) which is removed by a substitution reaction or elimination reaction when the functional group represented by the formula (2) reacts with a nucleophile or a base. _{3, -OSO 2 C 6 H 4} CH 3, -OCOCH 3, -OSO 3 -, a pyridinium).
Formula (3)

  In formula (3), X represents a single bond, —O—, or —NR—, and R represents a hydrogen atom, an alkyl group, or an aralkyl group. Y and Z represent a halogen atom (for example, chlorine atom, bromine atom), an alkoxy group (for example, methoxy), a hydroxyl group and a salt thereof, and an optionally substituted amino group, and at least one of Y and Z is a halogen atom. .

Formula (4): -CHO
Formula (5):

Formula (6): -NCO
Formula (7): —NHCONHCOCH═CH ₂
Formula (8): —NHCONHCOCH ₂ CH ₂ X
In formula, X is synonymous with X of Formula (2).
Formula (9): -COX
In the formula, X is a group (for example, easily leaving when the functional group represented by the formula (9) reacts with an amino group)

And formula (9) represents what is commonly known as an active ester group or mixed acid anhydride.

In producing the polymer hardener used in the present invention, the polymerization method is not particularly limited. For example, the polymer hardener may be produced by a condensation polymerization method, and may be a radical using a compound having an ethylenically unsaturated bond. You may manufacture by methods, such as superposition | polymerization and anionic polymerization. Furthermore, it may be produced by introducing the reactive functional group into a natural polymer (for example, starch, dextran, gelatin, etc.). There is no particular restriction on the method of introducing the functional group capable of reacting with the hydrophilic colloid used in the present invention (the functional group represented by the above formula (1) to formula (9), hereinafter referred to as the reactive functional group). A polymer may be produced by carrying out a polymerization reaction using a monomer having a reactive functional group, or the reactive functional group may be introduced by a so-called polymer reaction after the polymer has been produced in advance. . It is also effective to perform a polymerization reaction using a monomer compound having a precursor of a reactive functional group and then generate a reactive functional group by an appropriate method.

  The polymer hardener used in the present invention may be produced by radical polymerization of a monomer having the reactive functional group (or its precursor) and an ethylenically unsaturated bond in the same molecule. The following compounds are typical examples of the monomer having a reactive functional group.

  The polymer used in the present invention may be a homopolymer of a monomer having a reactive functional group, or may be a copolymer with one or more other monomers. In the case of a copolymer, the proportion of the monomer having a reactive functional group is 1% by mass or more, and preferably 5% by mass or more. In the case of radical copolymerization, other monomers are not particularly limited as long as radical polymerization is possible, but the following monomers can be given as specific examples. In addition, when other monomers have a functional group capable of reacting, a combination of monomers is appropriately selected within a range in which no reaction occurs with the functional groups represented by the above formulas (1) to (9). It is preferable.

Acrylic acid, methacrylic acid and esters thereof: for example, acrylic acid, methyl acrylate, butyl acrylate, benzyl acrylate, hydroxyethyl acrylate, CH ₂ ═CHCOO (CH ₂ CH ₂ O) _n R (R is a hydrogen atom, an alkyl group , N is an integer of 1 or more), methacrylic acid, methyl methacrylate, ethyl methacrylate, benzyl methacrylate, hydroxyethyl methacrylate, 2-ethylhexyl methacrylate, 2-methoxyethyl methacrylate, N, N-dimethylaminoethyl methacrylate, 2-sulfoethyl methacrylate etc,
Amides of ethylenically unsaturated carboxylic acids: acrylamide, methacrylamide, N-acryloylmorpholine, N, N-dimethylacrylamide, 2-acrylamido-2-methylpropanesulfonic acid (or a salt thereof), etc.
Aromatic monomers: styrene, vinyl toluene, pt-butyl styrene, p-vinyl benzoic acid, vinyl naphthalene, etc.
Other vinyl monomers: ethylene, propylene, vinyl chloride, vinylidene chloride, trifluoroethylene, trifluorochloroethylene, vinyl acetate, vinyl propionate, vinyl alcohol, N-vinyl pyrrolidone, N-vinyl acetamide, acrylonitrile, methacrylo Nitrile etc.

  Specific examples of the polymer hardener used in the present invention are shown below, but the present invention is not limited thereto. The copolymerization ratio of each compound represents a mass percentage ratio.

P-1: M-1 / 2-acrylamido-2-methylpropanesulfonic acid soda copolymer (10/90)
P-2: M-1 / 2-acrylamido-2-methylpropanesulfonic acid soda copolymer (30/70)
P-3: M-1 / 2-acrylamido-2-methylpropanesulfonic acid soda copolymer (50/50)
P-4: M-1 / methyl methacrylate copolymer (20/80)
P-5: M-2 / sodium acrylate copolymer (30/70)
P-6: M-2 / 2-hydroxyethyl methacrylate copolymer (20/80)
P-7: M-3 / butyl acrylate copolymer (60/40)
P-8: M-4 / 2-acrylamido-2-methylpropanesulfonic acid soda copolymer (30/70)
P-9: M-6 / ethyl acrylate copolymer (60/40)
P-10: M-7 / N-vinylpyrrolidone copolymer (20/80)

P-11: M-7 / diacetone acrylamide copolymer (10/90)
P-12: M-10 / sodium methacrylate copolymer (15/85)
P-13: M-10 / methyl acrylate / methyl methacrylate copolymer (20/40/40)
P-14: M-12 / ethyl methacrylate copolymer (33/67)
P-15: M-12 / 2-acrylamido-2-methylpropanesulfonic acid soda copolymer (15/85)
P-16: M-13 / methyl methacrylate copolymer (33/67)
P-17: M-13 / 2-acrylamido-2-methylpropanesulfonic acid soda copolymer (20/80)
P-18: M-13 / N-acryloylmorpholine copolymer (20/80)
P-19: M-13 / methoxy polyethylene glycol (23-mer) monomethacrylate copolymer (50/50)
P-20: M-18 / N, N-dimethylacrylamide copolymer (5/95)

P-21: M-18 / butyl methacrylate copolymer (30/70)
P-22: M-18 / styrene / butyl acrylate copolymer (20/30/50)
P-23: M-19 / 2-acrylamido-2-methylpropanesulfonic acid soda copolymer (20/80)
P-24: M-23 / methyl acrylate copolymer (20/80)
P-25: M-24 / ethyl acrylate / styrene copolymer (20/50/30)
P-26: M-26 / acrylamide copolymer (25/75)
P-27: M-26 / N, N-dimethylaminoethyl methacrylate copolymer (30/70)

  The reactive functional group of the polymer hardener used in the present invention is preferably an active olefin polymer hardener, s-triazine polymer hardener, active halogen polymer hardener, aldehyde. Type polymer hardeners, glycidyl type polymer hardeners, etc. are used, more preferably active olefin type polymer hardeners or precursors thereof, s-triazine type polymer hardeners, glycidyl type polymer hardeners. Filming agents are used, and vinylsulfone type polymer hardening agents or precursors thereof, and dichlorotriazine type polymer hardening agents are particularly preferable.

  In the present invention, the polymer hardener is intended to be immobilized on the biosensor surface to form a hydrogel. Therefore, it is desirable to have a hydrophilic group in addition to the reactive functional group. Specific examples of hydrophilic groups include nonionic groups such as hydroxyl groups and ethylene glycol groups, anionic groups such as sulfonic acid groups, carboxylic acids, and phosphoric acid groups, and cationic groups such as quaternary ammonium groups and pyridinium groups. Examples include zwitterionic groups such as groups.

In the present invention, examples of the monomer unit having a hydrophilic group include the following monomers.
Monomers having a nonionic group: 2-hydroxyethyl acrylate, 2-hydroxyethyl methacrylate, hydroxypropyl acrylate, hydroxypropyl methacrylate, 2-hydroxy-3-chloropropyl acrylate, β-hydroxyethyl-β′-acryloyloxyethyl phthalate, 1,4-butylene glycol monoacrylate, hydroxystyrene, allyl alcohol, methallyl alcohol, isopropenyl alcohol, 1-butenyl alcohol and the like.
Monomers having an anionic group: vinyl sulfonic acid, methallyl sulfonic acid, 2-acrylamido-2-methylpropane sulfonic acid, sulfoethyl methacrylate, styrene sulfonic acid, acrylic acid, methacrylic acid, 2- (phosphonoethyloxy) ethyl Methacrylate and the like.
Monomers having a cationic group: [2- (acryloyloxy) ethyl] trimethylammonium chloride, [2- (methacryloyloxy) ethyl] trimethylammonium chloride, etc.
Monomers having zwitterionic groups: [2- (methacryloyloxy) ethyl] dimethyl- (3-sulfopropyl) ammonium hydroxide, [2- (methacryloyloxy) ethyl] phosphorylcholine and the like.

By introducing a cationic group or an anionic group into the polymer hardener, it is possible to concentrate a physiologically active substance having an opposite charge to the detection surface using electrostatic interaction. For example, in the case of a protein dissolved in a buffer solution having a pH higher than the isoelectric point, since the polymer hardener having a cationic group is electrostatically concentrated on the bonded hydrogel surface, the reactive functional It becomes possible to combine with a group. On the other hand, in the case of a protein dissolved in a buffer solution having a pH lower than the isoelectric point, it is electrostatically concentrated on the surface of the hydrogel to which a polymer hardener having an anionic group is bonded, so that the reactive functional group is efficiently used. It becomes possible to combine with a group.

  In the present invention, a known method can be used as a method for bonding the polymer hardener as a binding matrix and the metal surface. Patent Document 1 discloses a method of binding a binding matrix to a metal surface via a hydrophobic polymer as described below in this specification (see Japanese Patent Application Laid-Open No. 2004-271514 and Japanese Patent Application No. 2004-225130). Application of the disclosed method of binding the binding matrix to the metal surface via a tightly packed monolayer of XR-Y (X is bound to the metal and Y is bound to the binding matrix) can do. Preferably, after forming a dense layer on the metal surface using alkanethiol having a reactive group at the terminal (or disulfide which is an oxidant thereof), the reactive group at the terminal of alkanethiol and the polymer hardener are used. It is a binding method to react.

  By bringing the bioactive substance into contact with the biosensor surface in the present invention, the reactive functional group of the polymer hardener and the bioactive substance are covalently bonded, so that the bioactive substance can be immobilized on the biosensor. It becomes. Further, when the amino acid solution is brought into contact with the biosensor surface, the reactive functional group of the polymer hardener and the amino group of the amino acid react with each other, and as a result, the reactive functional group is converted into a carboxylic acid. The surface of a biosensor having a carboxylic acid is activated by a known method, for example, 1- (3-Dimethylaminopropyl) -3 ethylcarbodiimide (EDC) and N-Hydroxysuccinimide (NHS) which are water-soluble carbodiimides. The active substance can be immobilized. As a method for activating carboxylic acid, the method described in Japanese Patent Application No. 2004-238396 (that is, any of uronium salt, phosphonium salt, or triazine derivative having a specific structure for the carboxyl group present on the surface of the substrate) And a method described in Japanese Patent Application No. 2004-275012 (that is, a carboxyl group present on the surface of a substrate is activated with a carbodiimide derivative or a salt thereof). And then esterifying with a nitrogen-containing heteroaromatic compound having a hydroxyl group, a phenol derivative having an electron-withdrawing group or an aromatic compound having a thiol group, and then reacting with an amine to form a carboxylic acid amide group. The forming method) can also be preferably used.

  The biosensor referred to in the present invention is interpreted in the broadest sense, and means a sensor that measures and detects a target substance by converting an interaction between biomolecules into a signal such as an electrical signal. A normal biosensor is composed of a receptor site for recognizing a chemical substance to be detected and a transducer site for converting a physical change or chemical change generated therein into an electrical signal. In the living body, there are enzymes / substrates, enzymes / coenzymes, antigens / antibodies, hormones / receptors and the like as substances having affinity for each other. Biosensors use the principle that one of these substances having affinity with each other is immobilized on a substrate and used as a molecular recognition substance, thereby selectively measuring the other substance to be matched.

  In the biosensor of the present invention, a metal surface or a metal film can be used as a substrate. The metal constituting the metal surface or metal film is not particularly limited as long as surface plasmon resonance can occur when, for example, a surface plasmon resonance biosensor is considered. Preferred examples include free electron metals such as gold, silver, copper, aluminum, and platinum, with gold being particularly preferred. These metals can be used alone or in combination. In consideration of adhesion to the substrate, an intervening layer made of chromium or the like may be provided between the substrate and the layer made of metal.

  Although the thickness of the metal film is arbitrary, for example, when considering use for a surface plasmon resonance biosensor, the thickness is preferably 0.1 nm to 500 nm, particularly preferably 1 nm to 200 nm. If it exceeds 500 nm, the surface plasmon phenomenon of the medium cannot be sufficiently detected. Moreover, when providing the intervening layer which consists of chromium etc., it is preferable that the thickness of the intervening layer is 0.1 to 10 nm.

  The metal film may be formed by a conventional method, for example, sputtering, vapor deposition, ion plating, electroplating, electroless plating, or the like.

  The metal film is preferably disposed on the substrate. Here, “arranged on the substrate” means that the metal film is arranged so as to be in direct contact with the substrate, and that the metal film is not directly in contact with the substrate, but through other layers. This also includes the case where they are arranged. As a substrate that can be used in the present invention, for example, in the case of a surface plasmon resonance biosensor, generally, optical glass such as BK7, or synthetic resin, specifically polymethyl methacrylate, polyethylene terephthalate, polycarbonate A material made of a material transparent to laser light such as a cycloolefin polymer can be used. Such a substrate is preferably made of a material that does not exhibit anisotropy with respect to polarized light and has excellent processability.

  In the present invention, the hydrophilic polymer having a reactive functional group capable of reacting with a hydroxyl group or amino group of a physiologically active substance is bonded to the metal layer directly or via an intermediate layer. As the intermediate layer, a layer made of a hydrophobic polymer compound or a self-assembled film can be used. Hereinafter, the hydrophobic polymer compound and the self-assembled film will be described.

  The hydrophobic polymer compound used in the present invention is a polymer compound having no water absorption, and its solubility in water (25 ° C.) is 10% or less, more preferably 1% or less, most preferably 0.1% or less. It is.

  Hydrophobic monomers that form hydrophobic polymer compounds include vinyl esters, acrylic acid esters, methacrylic acid esters, olefins, styrenes, crotonic acid esters, itaconic acid diesters, and maleic acid diesters. , Fumaric acid diesters, allyl compounds, vinyl ethers, vinyl ketones and the like. The hydrophobic polymer compound may be a homopolymer composed of one type of monomer or a copolymer composed of two or more types of monomers.

  Examples of the hydrophobic polymer compound preferably used in the present invention include polystyrene, polyethylene, polypropylene, polyethylene terephthalate, polyvinyl chloride, polymethyl methacrylate, polyester, and nylon.

  Coating of the hydrophobic polymer compound on the substrate can be performed by a conventional method, for example, spin coating, air knife coating, bar coating, blade coating, slide coating, curtain coating, spraying, vapor deposition, casting, It can be performed by an immersion method or the like.

  In the dipping method, coating is performed by bringing the substrate into contact with a hydrophobic polymer compound solution and then contacting the substrate with a solution not containing the hydrophobic polymer compound solution. Preferably, the solvent of the hydrophobic polymer compound solution and the solvent of the liquid not containing the hydrophobic polymer compound are the same solvent.

  In the dipping method, a hydrophobic polymer compound layer having a uniform coating thickness can be obtained on the surface of the substrate by appropriately selecting a solvent for coating the hydrophobic polymer compound, regardless of the unevenness, curvature, and shape of the substrate.

  The coating solvent for the dipping method is not particularly limited, and any solvent can be used as long as it dissolves a part of the hydrophobic polymer compound. For example, a formamide solvent such as N, N-dimethylformamide, a nitrile solvent such as acetonitrile, an alcohol solvent such as phenoxyethanol, a ketone solvent such as 2-butanone, and a benzene solvent such as toluene can be used. However, it is not limited to these.

  The solution of the hydrophobic polymer compound to be brought into contact with the substrate may be either a completely dissolved hydrophobic polymer compound or a suspension containing an insoluble component of the hydrophobic polymer compound. The liquid temperature is not particularly limited as long as a part of the hydrophobic polymer compound is dissolved, but is preferably −20 ° C. or higher and 100 ° C. or lower. The liquid temperature may be varied while the substrate is in contact with the hydrophobic polymer compound solution. Although there is no restriction | limiting in particular in the hydrophobic polymer compound density | concentration of a solution, Preferably it is 0.01 to 30%, More preferably, it is 0.1 to 10%.

  The time for bringing the solid substrate into contact with the hydrophobic polymer solution is not particularly limited, but is preferably 1 second to 24 hours, more preferably 3 seconds to 1 hour.

As a liquid not containing a hydrophobic polymer compound, the difference between the SP value of the solvent itself (unit: (J / cm ³ ) ^1/2 ) and the SP value of the hydrophobic polymer compound is 1 or more and 20 or less. Preferably, it is 3 or more and 15 or less. The SP value is represented by the square root of the cohesive energy density between molecules and is also called a solubility parameter. In the present invention, the SP value δ is calculated by the following formula. As the cohesive energy Ecoh and the molar volume V of each functional group, values defined by Fedors were used (R. F. Fedors, Polym. Eng. Sci., 14 (2), P147, P472 (1974)).
δ = (ΣEcoh / ΣV) ^1/2
By way of example, the SP values of hydrophobic polymer compounds and solvents are as follows: Polymethylmethacrylate-polystyrene copolymer (1: 1): for 21.0 Solvent 2-phenoxyethanol: 25.3, for Polymethylmethacrylate: 20.3 Solvent acetonitrile: 22.9, polystyrene: 21.6 with respect to polystyrene: 21.6.

  The time for contacting the substrate with the liquid not containing the hydrophobic polymer compound is not particularly limited, but is preferably 1 second to 24 hours, more preferably 3 seconds to 1 hour. The liquid temperature is not particularly limited as long as the solvent is in a liquid state, but is preferably −20 ° C. or higher and 100 ° C. or lower. The liquid temperature may be varied while the substrate is in contact with the solvent. When using a solvent that is difficult to volatilize, for the purpose of removing the solvent, the solvent may be replaced with a volatile solvent that dissolves each other after contacting the solvent.

  The coating thickness of the hydrophobic polymer compound is not particularly limited, but is preferably 0.1 nm to 500 nm, particularly preferably 1 nm to 300 nm.

  Next, the self-assembled film will be described. Sulfur compounds such as thiols and disulfides spontaneously adsorb on a noble metal substrate such as gold to give an ultra-thin film of single molecular size. The aggregate is called a self-assembled film because it shows an arrangement depending on the crystal lattice of the substrate and the molecular structure of adsorbed molecules. In the present invention, for example, as a self-assembling compound, 7-carboxy-1-heptanethiol, 10-carboxy-1-decanethiol, 4,4′-dithiodibutylic acid, 11-hydroxy-1-undecanethiol, 11 -Amino-1-undecanethiol and the like can be used.

  The biosensor of the present invention preferably has a functional group capable of immobilizing a physiologically active substance on the outermost surface of the substrate. The “outermost surface of the substrate” herein means “the side farthest from the substrate”, and more specifically, “the side farthest from the substrate in the compound coated on the substrate”.

  The sensor substrate obtained as described above has a physiologically active substance bonded to the metal surface or metal film by covalently bonding the physiologically active substance via Y which is a functional group in the general formula (A). Can be immobilized.

  The physiologically active substance immobilized on the sensor substrate of the present invention is not particularly limited as long as it interacts with the measurement object. For example, immune proteins, enzymes, microorganisms, nucleic acids, low molecular organic compounds, non-immune proteins And immunoglobulin binding proteins, sugar binding proteins, sugar chains that recognize sugars, fatty acids or fatty acid esters, polypeptides or oligopeptides having ligand binding ability, and the like.

  Examples of immunity proteins include antibodies and haptens that use the measurement target as an antigen. As the antibody, various immunoglobulins, that is, IgG, IgM, IgA, IgE, and IgD can be used. Specifically, when the measurement target is human serum albumin, an anti-human serum albumin antibody can be used as the antibody. In addition, when using pesticides, insecticides, methicillin-resistant Staphylococcus aureus, antibiotics, narcotics, cocaine, heroin, cracks, etc. as antigens, for example, anti-atrazine antibodies, anti-kanamycin antibodies, anti-methamphetamine antibodies, or pathogenic E. coli Among them, antibodies against O antigens 26, 86, 55, 111, 157 and the like can be used.

  The enzyme is not particularly limited as long as it shows activity against the measurement object or a substance metabolized from the measurement object, and various enzymes such as oxidoreductase, hydrolase, isomerase , A desorbing enzyme, a synthesizing enzyme and the like can be used. Specifically, if the measurement object is glucose, glucose oxidase can be used, and if the measurement object is cholesterol, cholesterol oxidase can be used. In addition, when pesticides, insecticides, methicillin-resistant Staphylococcus aureus, antibiotics, narcotics, cocaine, heroin, cracks, etc. are used as measurement objects, they exhibit specific reactions with substances metabolized from them, such as acetylcholinesterase. Enzymes such as catecholamine esterase, noradrenaline esterase and dopamine esterase can be used.

The microorganism is not particularly limited, and various microorganisms including Escherichia coli can be used.
As the nucleic acid, one that hybridizes complementarily with the nucleic acid to be measured can be used. As the nucleic acid, either DNA (including cDNA) or RNA can be used. The type of DNA is not particularly limited, and may be any of naturally derived DNA, recombinant DNA prepared by gene recombination technology, or chemically synthesized DNA.
Examples of the low molecular weight organic compound include any compound that can be synthesized by an ordinary organic chemical synthesis method.

The non-immune protein is not particularly limited, and for example, avidin (streptavidin), biotin or a receptor can be used.
As the immunoglobulin-binding protein, for example, protein A or protein G, rheumatoid factor (RF) and the like can be used.
Examples of sugar-binding proteins include lectins.
Examples of the fatty acid or fatty acid ester include stearic acid, arachidic acid, behenic acid, ethyl stearate, ethyl arachidate, and ethyl behenate.

  The biosensor on which a physiologically active substance is immobilized as described above can be used for detection and / or measurement of a substance that interacts with the physiologically active substance.

  In the present invention, it is preferable to detect and / or measure the interaction between the physiologically active substance immobilized on the sensor substrate and the test substance by a non-electrochemical method. Non-electrochemical methods include surface plasmon resonance (SPR) measurement technology, quartz crystal microbalance (QCM) measurement technology, measurement technology using functionalized surfaces from gold colloidal particles to ultrafine particles.

  According to a preferred aspect of the present invention, the biosensor of the present invention can be used as a surface plasmon resonance biosensor characterized by including a metal film disposed on a transparent substrate, for example.

  The surface plasmon resonance biosensor is a biosensor used in the surface plasmon resonance biosensor, and includes a part that transmits and reflects light emitted from the sensor, and a part that fixes a physiologically active substance. And may be fixed to the main body of the sensor or may be removable.

  The phenomenon of surface plasmon resonance is due to the fact that the intensity of monochromatic light reflected from the boundary between an optically transparent substance such as glass and the metal thin film layer depends on the refractive index of the sample on the metal exit side. Yes, so the sample can be analyzed by measuring the intensity of the reflected monochromatic light.

  As a surface plasmon measuring device for analyzing the characteristics of a substance to be measured using a phenomenon in which surface plasmons are excited by light waves, there is an apparatus using a system called Kretschmann arrangement (for example, JP-A-6-167443). See the official gazette). A surface plasmon measuring apparatus using the above system basically includes a dielectric block formed in a prism shape, for example, and a metal film formed on one surface of the dielectric block and brought into contact with a substance to be measured such as a sample liquid. A light source that generates a light beam; an optical system that causes the light beam to enter the dielectric block at various angles so that a total reflection condition is obtained at an interface between the dielectric block and the metal film; and It comprises light detecting means for detecting the surface plasmon resonance state, that is, the state of total reflection attenuation by measuring the intensity of the light beam totally reflected at the interface.

  In order to obtain various incident angles as described above, a relatively thin light beam may be incident on the interface by changing the incident angle, or a component incident on the light beam at various angles is included. As described above, a relatively thick light beam may be incident on the interface in a convergent light state or a divergent light state. In the former case, a light beam whose reflection angle changes according to the change in the incident angle of the incident light beam is detected by a small photodetector that moves in synchronization with the change in the reflection angle, or the direction in which the reflection angle changes Can be detected by an area sensor extending along the line. On the other hand, in the latter case, it can be detected by an area sensor extending in a direction in which each light beam reflected at various reflection angles can be received.

  In the surface plasmon measuring apparatus having the above configuration, when a light beam is incident on a metal film at a specific incident angle that is greater than the total reflection angle, an evanescent wave having an electric field distribution is generated in the measured substance in contact with the metal film. The evanescent wave excites surface plasmons at the interface between the metal film and the substance to be measured. When the wave number vector of the evanescent light is equal to the wave number of the surface plasmon and the wave number matching is established, both are in a resonance state and the energy of the light is transferred to the surface plasmon. The intensity of the reflected light decreases sharply. This decrease in light intensity is generally detected as a dark line by the light detection means. The resonance described above occurs only when the incident beam is p-polarized light. Therefore, it is necessary to set in advance so that the light beam is incident as p-polarized light.

  If the wave number of the surface plasmon is known from the incident angle at which this total reflection attenuation (ATR) occurs, that is, the total reflection attenuation angle (θSP), the dielectric constant of the substance to be measured can be obtained. In this type of surface plasmon measurement apparatus, as shown in Japanese Patent Application Laid-Open No. 11-326194, in order to measure the total reflection attenuation angle (θSP) with high accuracy and a large dynamic range, It is considered to use detection means. This light detection means is provided with a plurality of light receiving elements arranged in a predetermined direction, and arranged so that different light receiving elements receive light beam components totally reflected at various reflection angles at the interface. Is.

  In that case, there is provided differential means for differentiating the light detection signals output from the light receiving elements of the arrayed light detection means with respect to the arrangement direction of the light receiving elements, and based on the differential value output by the differential means. In many cases, the total reflection attenuation angle (θSP) is specified to obtain a characteristic related to the refractive index of the substance to be measured.

  Moreover, as a similar measuring device using total reflection attenuation (ATR), for example, “Spectroscopic Research” Vol. 47, No. 1, (1998), pages 21 to 23 and pages 26 to 27 are described. Devices are also known. This leakage mode measuring device is basically a dielectric block formed in a prism shape, for example, a clad layer formed on one surface of the dielectric block, and formed on the clad layer to be in contact with the sample liquid. Optical waveguide layer to be generated, a light source for generating a light beam, and the light beam to the dielectric block at various angles so that a total reflection condition is obtained at the interface between the dielectric block and the cladding layer. The optical system includes an incident optical system and light detection means for detecting the excitation state of the waveguide mode, that is, the total reflection attenuation state by measuring the intensity of the light beam totally reflected at the interface.

  In the leakage mode measuring apparatus having the above-described configuration, when a light beam is incident on the cladding layer through the dielectric block at an incident angle greater than the total reflection angle, the light waveguide layer transmits a specific wave number after passing through the cladding layer. Only light having a specific incident angle having a wave length propagates in the waveguide mode. When the waveguide mode is excited in this way, most of the incident light is taken into the optical waveguide layer, resulting in total reflection attenuation in which the intensity of light totally reflected at the interface is sharply reduced. Since the wave number of guided light depends on the refractive index of the substance to be measured on the optical waveguide layer, knowing the specific incident angle at which total reflection attenuation occurs, the refractive index of the substance to be measured and the measurement object related thereto The properties of the substance can be analyzed.

  In this leakage mode measuring apparatus, the above-mentioned array-shaped light detecting means can be used to detect the position of the dark line generated in the reflected light due to the total reflection attenuation, and the above-described differentiating means is applied in conjunction therewith. Often done.

  In addition, the surface plasmon measurement device and the leakage mode measurement device described above may be used for random screening to find a specific substance that binds to a desired sensing substance in the field of drug discovery research. In this case, the thin film layer A sensing substance is fixed on the sensing substance on the sensing substance (a metal film in the case of a surface plasmon measuring apparatus, a clad layer and an optical waveguide layer in the case of a leakage mode measuring apparatus), and various analytes are placed on the sensing substance. A sample solution dissolved in a solvent is added, and the total reflection attenuation angle (θSP) is measured every time a predetermined time elapses.

  If the analyte in the sample liquid binds to the sensing substance, the refractive index of the sensing substance changes with time due to this binding. Therefore, by measuring the total reflection attenuation angle (θSP) every predetermined time and measuring whether or not the total reflection attenuation angle (θSP) has changed, the binding state of the analyte and the sensing substance is determined. It is possible to determine whether or not the analyte is a specific substance that binds to the sensing substance based on the result. Examples of the combination of the specific substance and the sensing substance include an antigen and an antibody, or an antibody and an antibody. Specifically, a rabbit anti-human IgG antibody can be immobilized on the surface of the thin film layer as a sensing substance, and a human IgG antibody can be used as the specific substance.

  Note that in order to measure the binding state between the subject and the sensing substance, it is not always necessary to detect the angle of total reflection attenuation (θSP) itself. For example, a sample solution can be added to the sensing substance, and the amount of change in the total reflection attenuation angle (θSP) thereafter can be measured, and the binding state can be measured based on the magnitude of the angle change. If the above-described arrayed light detecting means and differentiating means are applied to a measuring device using total reflection attenuation, the change amount of the differential value reflects the angle change amount of the total reflection attenuation angle (θSP). Therefore, the binding state between the sensing substance and the analyte can be measured based on the amount of change in the differential value (see Japanese Patent Application No. 2000-398309 by the present applicant). In such a measurement method and apparatus using total reflection attenuation, a sample liquid consisting of a solvent and an analyte is placed on a cup-shaped or petri-shaped measuring chip in which a sensing substance is fixed on a thin film layer formed in advance on the bottom surface. The amount of change in angle of the total reflection attenuation angle (θSP) described above is measured.

  Furthermore, a measuring apparatus using total reflection attenuation capable of measuring a large number of samples in a short time by sequentially measuring a plurality of measuring chips mounted on a turntable or the like is disclosed in JP-A-2001-2001. No. 330560.

When the biosensor of the present invention is used for surface plasmon resonance analysis, it can be applied as a part of various surface plasmon measurement devices as described above.
The following examples further illustrate the present invention, but the scope of the present invention is not limited to these examples.

Example 1:
The present example is a method for producing a sensor chip using a hydrophilic polymer (polymer hardener) having a reactive functional group capable of reacting with a hydroxyl group or amino group of a physiologically active substance.
(1) Production of Gold Surface Substrate Chrome on a substrate using a parallel plate type 6-inch sputtering apparatus (SH-550 manufactured by ULVAC, Inc.) on a glass substrate having a length of 8 mm, a width of 80 mm, and a thickness of 0.5 mm. The thickness of 1 nm,
Further, a sputter film was formed on chromium so that the thickness of gold was 50 nm. This substrate was treated with Model-208UV-ozone cleaning system (TECHNOVISION INC.) For 30 minutes to produce a gold surface substrate.

(2) Preparation of Sample 1 (Comparative Example) A hydrogel was prepared on the gold surface by applying the method described in Patent Document 1. The gold surface substrate prepared in (1) was placed in a Petri dish (inner diameter 16 cm). Ethanol / water (80/20) in which 5.0 mM 11-hydroxyundecanthiol (manufactured by Dojin Chemical) was dissolved was poured onto the surface. The Petri dish was incubated for 20 minutes in a 40 ° C. shaking incubator. The surface was washed with 5 × 50 ml water, 50 ml ethanol / water (80/20), and 5 × 50 ml water. In addition, contact was made with a solution of 2.0 ml epichlorohydrin in 20 ml 0.4 M sodium hydroxide and 20 ml diethylene glycol dimethyl ether. The reaction was allowed to proceed for 4 hours in a shaking incubator at 25 ° C. The surface was washed with 2 × 50 ml ethanol and 5 × 50 ml water. 13.5 g dextran (T500, Pharmacia) was dissolved in 40.5 ml water and a solution with 4.5 ml 1M sodium hydroxide added was poured onto the epichlorohydrin treated surface. Next, after incubation for 20 hours in a shaking incubator at 25 ° C., the surface was washed with 15 × 50 ml of 50 ° C. water. 3.5 g of bromoacetic acid was dissolved in 27 g of 2M sodium hydroxide solution, poured onto a dextran-treated surface, incubated for 16 hours in a shaking incubator at 28 ° C., and then washed with water. Sample 1 was obtained by repeating the reaction with the bromoacetic acid solution, incubation at 28 ° C. for 16 hours, and washing with water again.

(3) Preparation of Sample 2 The gold surface substrate prepared in (1) was placed in a Petri dish (inner diameter 16 cm). Pour ethanol / water (80/20) in which 4.0 mM 8-hydroxyoctanethiol (manufactured by Dojindo Chemical Co., Ltd.) and 1.0 mM 11-aminoundecanethiol (manufactured by Dojindo Chemical Co., Ltd.) were dissolved, and shake the Petri dish at 40 ° C. Incubated for 20 minutes in incubator. The surface was washed with 5 × 50 ml water, 50 ml ethanol / water (80/20), and 5 × 50 ml water. An alkaline solution (pH 10.0, adjusted with NaOH) in which 10% by mass of the polymer hardener P-6 was dissolved was poured onto the surface, and the Petri dish was incubated in a shaking incubator at 60 ° C. for 16 hours. Sample 2 was obtained by washing the surface with 5 × 50 ml of water.

(4) Preparation of sample 3 Sample 3 was obtained by performing the same operation except that the polymer hardener P-6 of sample 2 was changed to the polymer hardener P-10.

(5) Preparation of sample 4 1M glycine aqueous solution (pH 8.5, pH adjusted with NaOH) was poured onto the surface obtained by the same operation as sample 2, and the Petri dish was incubated for 16 hours in a shaking incubator at 60 ° C. . Sample 4 was obtained by washing the surface with 5 × 50 ml of water.

(6) Preparation of Sample 5 A 1M aqueous glycine solution (pH 8.5, pH adjusted with NaOH) was poured onto the surface obtained in the same manner as Sample 3, and the Petri dish was incubated for 16 hours in a 60 ° C. shaking incubator. . Sample 5 was obtained by washing the surface with 5 × 50 ml of water.

(7) Preparation of Sample 6 1M 5-aminovaleric acid aqueous solution (pH 8.5, pH adjusted with NaOH) was poured onto the surface obtained in the same manner as Sample 2, and the Petri dish was shaken at 60 ° C. in a shaker incubator. Incubated for 16 hours. Sample 6 was obtained by washing the surface with 5 × 50 ml of water.

(8) Preparation of Sample 7 1M 5-aminovaleric acid aqueous solution (pH 8.5, pH adjusted with NaOH) was poured onto the surface obtained in the same manner as Sample 3, and the Petri dish was shaken at 60 ° C. in a shaker incubator. Incubated for 16 hours. Sample 7 was obtained by washing the surface with 5 × 50 ml of water.

Example 2
This example relates to the immobilization of neutral avidin (manufactured by PIERCE) to the sensor chip obtained in Example 1.
The sensor chips 1 and 4 to 7 manufactured in Example 1 were contacted with an aqueous solution containing 0.4 M EDC (1- (3-Dimethylaminopropyl) -3 ethylcarbodiimide) and 0.1 M NHS (N-Hydroxysuccinimide) for 30 minutes. And then washed with HBS-N buffer (Biacore, pH 7.4). The composition of the HBS-N buffer is HEPES (N-2-Hydroxyethylpiperazine-N′-2-ethanesulfonic acid) 0.01 mol / l (pH 7.4) and NaCl 0.15 mol / l. Next, the sensor chips 1 to 7 were installed in the surface plasmon resonance apparatus of the present invention. The sensor chip was set at a center position where the laser light hits in the center in the vertical direction and 40 mm from the end in the horizontal direction. By covering the chip with a polypropylene member, a cell having a width (longitudinal direction) of 1 mm, a length (horizontal method) of 7.5 mm, and a depth of 1 mm was produced. The inside of the cell was replaced with a neutral avidin solution (100 μg / ml, HBS-N buffer), allowed to stand for 30 minutes, and then replaced with HBS-N buffer. Through the above operation, N-avidin was immobilized on the sensor chip surface by covalent bond. For NHS esterified sensor chip 1, before and after the addition of neutral avidin, the amount of change in resonance signal (RU value) 3 minutes after the end of HBS-N buffer replacement was used as a reference for the binding amount of sensor chips 2-7. The amount of change in the resonance signal (RU value) before and after the addition of neutral avidin and 3 minutes after the completion of HBS-N buffer substitution (ie, the binding amount of neutral avidin) was evaluated as a relative value. The obtained results are shown in Table 1.

Example 3
This example relates to an interaction measurement between the sensor chips 1 to 7 on which neutral avidin obtained in Example 2 is immobilized and D-biotin (manufactured by Nacalai Tesque).
After the measurement in Example 2, the inside of the cell was replaced with an ethanolamine / HCl solution (1M, pH 8.5) to block activated COOH groups remaining without reacting with neutral avidin. Next, the inside of the cell was replaced with D-biotin (1 μg / ml, HBS-N buffer), allowed to stand for 10 minutes, and then replaced with HBS-N buffer.

  For sensor chip 1, the amount of change in resonance signal (RU value) before addition of D-biotin and 3 minutes after washing was used as a reference for the amount of binding, and before addition of D-biotin of sensor chip 2-7 and washing The amount of change in the resonance signal (RU value) after 3 minutes (that is, the amount of D-biotin bound) was evaluated as a relative value. The obtained results are shown in Table 1.

  According to this example, after forming a dense layer on the metal surface using an alkanethiol having an amino group at the terminal and an alkanethiol having a hydroxyl group at the terminal, the amino group and the polymer hardener are reacted. It was proved that sensor chips 2 and 3 capable of immobilizing N-avidin could be obtained without using epichlorohydrin and bromoacetic acid, which are simple and uneasy about safety. Furthermore, it was proved that the amount of N-avidin immobilized can be increased by reacting the reactive functional group on the surface of the sensor chip with an amino acid and activating with EDC / NHS (sensor chips 4 to 7). When using glycine as the amino acid (sensor chips 4 and 5), using 5-aminovaleric acid as the amino acid (sensor chips 6 and 7) increases the amount of N-avidin immobilized. It was proved that more N-avidin could be immobilized than Comparative Example 1 (sensor chip 1).

Since the amount of D-biotin bound to the sensor chip on which N-avidin is immobilized is substantially proportional to the amount of N-avidin immobilized, it was immobilized on the sensor chip obtained in the present invention. It has been demonstrated that the protein maintains its ability to bind low molecular weight compounds.

Claims (11)

A biosensor comprising a substrate having a metal layer on a surface and a hydrophilic polymer having a vinylsulfone group or a precursor thereof or a dichlorotriazine group bonded to the metal layer directly or via an intermediate layer. After forming a dense layer on the metal surface using a disulfide which is an alkanethiol having a reactive group at its terminal or its oxidized form, the reactive group at the terminal of the alkanethiol and a vinyl sulfone group or its precursor or dichlorotriazine The biosensor according to claim 1 , obtained by reacting a hydrophilic polymer having a group . The biosensor according to claim 1 or 2 , wherein a carboxylic acid is introduced by reacting a vinyl sulfone group or a precursor thereof or a dichlorotriazine group with an amino acid. The biosensor according to any one of claims 1 to 3 , wherein the thickness of the intermediate layer is 0.1 nm or more and 500 nm or less. The biosensor according to any one of claims 1 to 4 , wherein the metal is gold, silver, copper, platinum, or aluminum. The biosensor according to any one of claims 1 to 5 , which is used for surface plasmon resonance analysis. The method includes chemically bonding a hydrophilic polymer having a vinyl sulfone group or a precursor thereof or a dichlorotriazine group directly or via an intermediate layer to the surface of a substrate having a metal layer on the surface. 7. A method for producing a biosensor as described in any one of 6 above. The biosensor according to any one of claims 1 to 6 , wherein a physiologically active substance is covalently bonded to a carboxylic acid introduced by reacting a vinyl sulfone group or a precursor thereof or a dichlorotriazine group with an amino acid. The biosensor according to any one of claims 1 to 6 is brought into contact with the physiologically active substance, and the physiologically active substance is immobilized on the biosensor, comprising the step of binding the physiologically active substance to the surface of the biosensor. Method. Detecting or measuring a substance that interacts with the bioactive substance, comprising the step of bringing the biosensor according to any one of claims 1 to 6 into contact with the test substance, wherein the bioactive substance is covalently bonded to the surface. how to. The method according to claim 10, wherein a substance that interacts with a physiologically active substance is detected or measured by surface plasmon resonance analysis.