Patent Application
20070000776
1. Field of the Invention
The present invention relates to a biosensor. More precisely, the invention relates to a biosensor usable in blood sugar meters for household self-diagnosis, urine sugar meters, glycosylation hemoglobin meters, lactate meters, cholesterol meters, urate meters, protein meters, single nucleotide polymorphisms sensors, DNA chips for genetic diagnosis, as well as in alcoholic meters, glutamate meters, pyruvate meters and pH meters, in which the component concentration of various fluids is electrochemically determined by the use of enzyme or the like. The invention also relates to a method for producing a biosensor, comprising a folding and bending step. More precisely, the invention relates to the production method that preferably comprises a folding and bending step and a cutting step, or a folding and bending step and a fixation step.
2. Description of the Related Art
For disposable sensors (Patent Document 1, JP-A-47-500, Patent Document 3: JP-A-52-142584), heretofore known is a sensor mechanism (
Documents relating to the biosensor are listed below, along with the keywords therein:
Patent Document 1: JP-A-47-500 (Miles)
disposable sensor, dry reagent
Patent Document 2: JP-A-48-37187 (Roche)
enzyme, mediator
Patent Document 3: JP-A-52-142584 (Kodak)
disposable sensor
Patent Document 4: JP-A-54-50396 (Matsushita)
enzyme, mediator
Patent Document 5: JP-A-56-79242 (United)
capillary
Patent Document 6: JP-T 61-502419 (Unilever)
capillary
Patent Document 7: JP-A-1-291153 (Matsushita)
basic structure, sample inlet port, multi-detection sensor
Patent Document 8: JP-A-3-202764 (Matsushita)
basic structure, blood cell filtration membrane
Patent Document 9: JP-A-5-199898 (Toshiba)
DNA chip
Patent Document 10: JP-A-9-222414 (NOK)
pH sensor
Patent Document 11: JP-A-2001-204494
glycosylation hemoglobin sensor
Patent Document 12: WO01/33216 A1 (Serasense)
facing electrode, sample inlet port
Patent Document 13: U.S. Pat. No. 4,225,410 (Technicon)
array electrode
Patent Document 14: U.S. Pat. No. 5,653,864 (NOK)
protein sensor
Patent Document 15: U.S. Pat. No. 6,071,391 (NOK)
sample inlet port, facing electrode
Non-Patent Document 1: A. Ahmadian et al., Biotechniques, 32, 748 (2002)
SNPs
The above-mentioned conventional sensors require many steps and many materials for their production, and must have complicated structures. As a result, the production line for them requires a great deal of capital investment, the producibility of the products is not good, and the production costs are high. Naturally, the environmental load in preparing the materials and producing the products is great. Further, regarding their properties, since the sensors are produced in a process of complicated steps (in particular, for accurate positioning in forming constitutive elements on a substrate), they are unsatisfactory in point of the coefficient of variation (CV) thereof as an index of the fluctuation or distribution of the sensor characteristics of the products produced. In addition, since the shape change of a biosensor causes the reduction in the measurement accuracy and reproducibility thereof, the biosensor is desired to keep long-term shape stability with no warping or deformation of the cover and others thereof after production.
To solve the above-mentioned problems, the invention provides a biosensor produced by folding or bending or folding and bending a sheet of an electrically-insulating flat substrate.
Biosensor
The biosensor of the invention may comprise an electrode disposed in a space sandwiched between a substrate and a cover, a sample inlet port for injecting a sample into the space, and a sample transfer path extending from the sample inlet port to pass through the electrode, in which the substrate and the cover are formed by folding and bending a sheet of an electrically-insulating plate member, the electrode is fixed on the surface of the plate member, the plate member is folded and bent with its surface inside it so that the electrode is disposed in the space sandwiched between the substrate and the cover, and the sample transfer path is disposed on the surface of the plate member and is defined by an adhesive layer for face-to-face disposing the substrate and the cover.
According to the invention, an electrode and an adhesive layer are formed on the surface of a sheet of an electrically-insulating plate member, and the plate member is folded and bent to produce a biosensor in a simple manner.
In the above, for more simply producing the biosensor, perforations may be formed along the part of the plate member along which the plate member is to be folded and bent.
The biosensor of the invention may comprise a sensor body formed by bending a sheet of electrically-insulating plate member in a cylindrical structure, an electrode disposed on the inner wall of the sensor body, a sample inlet port formed on one end or the side face of the cylinder, and a sample transfer path extending from the sample inlet port to pass through the electrode. The cylindrical structure may be columnar, oval-columnar, semicircle-columnar, fan-columnar, crescent-columnar, triangle-columnar, square-columnar or polygon-columnar.
According to the invention, an electrode may be fixed on the surface of a sheet of an electrically-insulating plate member and the plate member may be worked into a cylinder structure, whereby a cylindrical biosensor equipped with a sample transfer path may be produced.
The invention also provides a biosensor having a reagent layer provided on the electrode or the cover through which a sample transfer path passes. According to the invention, the sample fed from the sample transfer path may be kept in contact with the reagent layer on the electrode or on the cover, and the sample is thus reacted with the reagent. This reactor is monitored as an electrical change at the electrode.
The sample inlet port may be on one end or in an intermediate point of the sample transfer path so far as it is in a position in which a sample may be injected into the sample transfer path.
In the invention, a surfactant and/or a lipid may be applied around the sample inlet port, or to or around the surface of the sample transfer path and the reagent layer. Coated with a surfactant or a lipid, the area enables smooth travel of the sample around it. For the lipid, preferred is lecithin. For coating with it, the lipid is preferably dissolved in a solvent. When lecithin is used, then the solvent for it is preferably 2-butanol. The sample inlet port may be so designed that its tip has a curved part.
The plate member may be selected from any of plastics, biodegradable materials or paper, so far as it is electrically insulating. One preferred example of the plastics is polyethylene terephthalate.
The electrode may be formed of any of carbon, silver, silver/silver chloride, platinum, gold, nickel, copper, palladium, titanium, iridium, lead, tin oxide or platinum black. The carbon may be selected from any of carbon nanotubes, carbon microcoils, carbon nanohorns, fullerenes, dendrimers or their derivatives. The electrode may be formed on the plate member by any of a screen-printing process, a vapor deposition process, a sputtering process, a foil-sticking process, or a plating process.
The electrode may be defined by a resist layer. The resist layer may be formed according to a screen-printing process.
The adhesive layer may also be formed according to a screen-printing process. The adhesive is preferably an acrylic resin, more preferably a thermosetting resin or a photocurable resin, even more preferably a visible ray-curable acrylic resin.
The reagent layer may be formed according to a screen-printing process or a dispenser process; and the fixation of the reagent layer to the electrode surface, the plate member surface or the cover may be effected according to a drying-accompanied adsorption or covalent-bonding process.
Preferably, the reagent layer is formed after purification. For the purification, for example, the reagent may be filtered through a membrane. Through the purification, impurities may be removed from the reagent.
Not limited to in one position, but the reagent layer may be disposed in two or more positions. In such a case, two or more different types of reagent layers may be provided. When such reagent layers are formed in two or more positions, then a convex partition may be provided between them. The convex partition may be formed according to a screen-printing process. The convex partition may be formed of any of carbon, resist or water-absorbent material.
The reagent layer may contain any of enzyme, antibody, nucleic acid, primer, peptide nucleic acid, nucleic acid probe, microorganism, organelle, receptor, cell tissue, molecule identification element such as crown ether, mediator, intercalator, coenzyme, labeled antibody substance, substrate, inorganic salt, surfactant, lipid, or their combinations. The enzyme may be any of an oxidase or dehydrogenase enzyme such as glucose oxidase, fructosylamine oxidase, lactate oxidase, urate oxidase, cholesterol oxidase, alcohol oxidase, glutamate oxidase, pyruvate oxidase, glucose dehydrogenase, lactate dehydrogenase, alcohol dehydrogenase, as well as cholesterol esterase, protease, DNA polymerase, or their combinations.
The reagent layer may contain not only enzyme alone but also a combination of enzyme and mediator. The mediator may be selected from potassium ferricyanide, ferrocene and benzoquinone. The reagent layer contains a combination of an inorganic salt such as sodium chloride or potassium chloride, and quinhydrone.
The reagent layer may contain a combination of primer, DNA polymerase and deoxyribonucleotide triphosphate. Further, the reagent layer may contain a combination of an inorganic salt such as sodium chloride or potassium chloride, and quinhydrone, as combined with primer, DNA polymerase and deoxyribonucleotide triphosphate.
When the biosensor is used as a DNA chip, then a nucleic acid probe is preferably immobilized as a reagent layer therein.
The invention relates to a biosensor device comprising the biosensor of the invention as above, a measuring unit for measuring an electric value at the electrode of the biosensor, and a display unit for displaying the value measured at the measuring unit. For the measuring method at the measuring unit, employable is any of potential step chronoamperometry, coulometry or cyclic voltammetry. The device may have a bluetooth mounted therein as a wireless unit.
Method for Producing Biosensor
A method for producing the biosensor of the invention is for producing a biosensor which comprises an electrode disposed in a space sandwiched between a substrate and a cover, a sample inlet port for injecting a sample into the space, and a sample transfer path extending from the sample inlet port to pass through the electrode and in which the sample transfer path is defined by an adhesive layer for face-to-face disposing the substrate and the cover;, and the method is characterized by comprising a folding and bending step of a plate member that is as follows:
A step of forming a substrate and a cover from a sheet of electrically-insulating plate member by folding and bending the plate member such that the electrode formed on the surface of the plate member could face inside thereof, to thereby dispose the electrode in the space sandwiched between the substrate and the cover.
According to the production method, a biosensor can be produced in a simple manner. The method of forming the electrode and the adhesive layer (sample transfer path) is as mentioned hereinabove.
The method for producing the biosensor of the invention may comprise the above-mentioned folding and bending step, and a step of cutting a foldable part to be a folded and bent site of the plate member.
In this description, the “folded part” means a folded and bent site of a plate member.
Since the folded part is cut, the stress to the folded part may be removed, and the adhesion between the substrate and the cover may be kept firm and tight for a long period of time.
Preferably, the cutting at the folded part is attained along perforations formed in the part. For the cutting, for example, employable is a method of folding the part and cutting it with a surgical knife along the perforations.
The method for producing the biosensor of the invention preferably includes a folding and bending step for the plate member, and a step of fixing the substrate and the cover by compression or modification working of the substrate or the cover, or application of a curing agent or a thermal-shrinking agent to the folded part, or fitting of a fixation tool (fixation step).
The compression, the modification working, the application of a curing agent or a thermal-shrinking agent, or the fitting of a fixation tool may be carried out singly or as combined.
The method for producing the biosensor of the invention includes a step of folding and bending a sheet of a plate member to form a substrate and a cover. In this, therefore, just after the plate member has been folded and bent, the folded and bent site (folded part) of the plate member may be restored to its original condition and the substrate or the cover may be warped or deformed. Accordingly, the method includes the above-mentioned fixation step, in which the substrate or the cover is prevented from warping or deforming.
The fixation method may comprise compression or modification working of the substrate or the cover, or application of a curing agent or a thermal-shrinking agent, or fitting of a fixation tool.
<Compression>
Compression is a method of fixing at least a part of the biosensor under pressure. The pressure to be applied to the substrate or the cover may be any one that is uniform and does not break the biosensor.
<Modification Working>
Modification working means a method of modifying the physical properties of the constitutive members of the biosensor or the physical properties of the materials added to the constitutive members of the biosensor, by heat, light or chemicals applied thereto. The modification working may remove or reduce the warping stress applied to the folded part, and may prevent the substrate or the cover from being warped and deformed.
Modification working methods (1) to (4) employable in the invention are mentioned below.
(1) Modification Working by Heat or Thermal Compression:
[1] Method of heating or thermally fixing under pressure the folded part of the biosensor or the folded part and around it thereof, or any other part of the biosensor.
According to the thermal modification, for example, the folded and bend site (folded part) of the folded and bent plate member, or the folded part and around it may be overheated by the use of a mold having the same shape as that of the folded part, whereby the member itself of the folded part may be modified and the warping force applied to it may be removed. In place of using such a mold, hot wires may also be used for modifying the folded part.
The “other part of the biosensor” is preferably the surface thereof above the substrate and cover surface, not having a reagent layer just below it. The heating method is preferably for exposing the site not having a reagent layer to heat by the use of the above-mentioned mold or hot wire to thereby modify the intended part of the member.
The method of thermal fixation under pressure is also preferably effected in the same manner as that of the heating method as above. Briefly, a hot mold is pressed against the intended site from above or below the substrate surface of the biosensor or from both the two thereof.
The temperature for the heating or thermal fixation under pressure may vary depending on the material of the plate member, but is generally preferably from 50 to 300° C., more preferably from 50 to 150° C.
[2] The adhesive layer of the biosensor contains a thermosetting resin, and the modification working is according to a method of heating or thermally fixing under pressure the folded part of the biosensor or the folded part and around it thereof, or any other part of the biosensor, thereby to cure all or a part of the adhesive layer.
When the biosensor of the invention has an adhesive layer, then a thermosetting resin is mixed in the adhesive layer or a thermosetting resin itself is used as the adhesive in the layer, and the plate member is folded and bent to form a biosensor, and thereafter this is subjected to the above-mentioned treatment of heating or thermal fixation under pressure.
In this case, the thermosetting resin includes, for example, epoxy resin, urea resin, melamine resin, phenolic resin, acrylic resin. Of those, acrylic resin is preferred. The epoxy resin may serve also as the adhesive itself in the layer.
A crosslinking agent and a polymerization initiator may be suitably added to the layer along with the thermosetting resin therein.
(2) Modification Working by Light.
[1] The plate member for the biosensor comprises a light-transmitting material, and the adhesive layer contains a photocurable resin, and the modification working is effected by irradiating the biosensor with light to thereby cure the adhesive layer.
When the biosensor of the invention has an adhesive layer, then a photocurable resin is mixed with the adhesive layer, or a photocurable resin itself is used to form the adhesive layer, and the plate member is folded and bent to form a biosensor, and thereafter the adhesive layer is irradiated with light and the photocurable resin is thereby cured. In this case, the plate member to form the substrate and the cover must be formed of a light-transmitting material. The light-transmitting material includes, for example, polyvinyl chloride, polycarbonate, polyester, polyethylene terephthalate. Preferably, the light irradiation is effected principally at the folded part as the center for it.
The photocurable resin includes, for example, UV-curable epoxy resin, UV-curable acrylic resin, UV-curable silicone resin, UV-curable silicone gel, delayed photocurable resin, visible ray-curable resin for dental use, visible ray-curable acrylic resin. Of those, the UV-curable acrylic resin, the delayed photocurable resin and the visible ray-curable acrylic resin may serve also as an adhesive itself.
A crosslinking agent and a polymerization initiator may be suitably added to the layer, along with the photocurable resin therein.
The light for irradiation varies depending on the type of the photocurable resin used. For example, when a UV-curable resin is used, then UV rays may be used for it; and when a visible ray-curable resin is used, then visible light may be used for it. For the light irradiation, employable are a heavy hydrogen lamp, a high-pressure mercury lamp, a low-pressure mercury lamp, a metal halide lamp and a non-electrode UV lamp for UV rays; and for visible rays, employable are a halogen lamp, a xenon lamp, a metal halide lamp, an incandescent lamp (tungsten lamp), a fluorescent lamp, a light-emitting diode and an organic light-emitting device.
The type of the light-transmitting plate member varies, depending on the type of the light used for it. For example, it includes polyvinyl chloride, polycarbonate, polyester, polyethylene terephthalate.
(3) When the Plate Member Itself is a Thermally or Optically-Modifying Material, the Following Methods are Employable.
[1] The plate member of the biosensor contains a thermosetting resin, and the modification working is attained by heating and curing all or a part of the plate member.
[2] The plate member of the biosensor contains a photocurable resin, and the modification working is attained by irradiating the plate member with light and curing it.
In addition, the plate member itself may be formed of a thermosetting resin or a photocurable resin. When the plate member is formed of a thermosetting resin, then the biosensor is formed by folding and bending, and thereafter the folded part or the folded part and around it or any other part of the biosensor is heated or thermally fixed under pressure, as in the above (1)[1]. In this, the thermosetting resin may be the same as in the above.
When the plate member is formed of a photocurable resin, then the biosensor is formed by folding and bending, and thereafter it is irradiated with light in the same manner as in the above (2) [1]. In this, the photocurable resin may be the same as in the above.
(4) A Solvent May be Infiltrated into the Folded Part in the Manner as Follows:
[1] A solvent is applied to the surface of the folded part of a biosensor, or to the surface of the folded part and around it, to thereby make the solvent infiltrated into it.
In this case, a solvent is applied to the folded part or to the folded part and around it, whereby the solvent is infiltrated into the plate member, and the warping force remaining in the plate member may be removed or reduced.
The solvent may be any one capable of being infiltrated into the plate member. Though depending on the material of the plate member, an organic solvent is preferred. Some examples of preferred combinations of the plate member and an organic solvent for it are mentioned below.
As in the above, the biosensor of the invention is preferably modified and worked according to the method mentioned above.
<Application of Curing Agent or Thermal-Shrinking Agent>
Application of a curing agent or a thermal-shrinking agent to the folded part is a method of applying a curing agent of a thermal-shrinking agent to the folded part of the constitutive member of the biosensor, and curing the curing agent or semi-curing the thermal-shrinking agent. According to the method, the warping stress given to the folded part may be depressed and the substrate and the cover may be prevented from being warped and deformed.
(1) A method of coating the folded part with a solidifying agent (thermosetting resin or photocurable resin) or a thermal-shrinking agent.
[1] A method comprising applying a thermosetting resin to the folded part of the biosensor or to the folded part and around it, then heating the thermosetting resin to cure it.
[2] A method comprising applying a photocurable resin to the folded part of the biosensor or to the folded part and around it, then irradiating the photocurable resin with light to cure it.
[3] A method comprising applying a thermal-shrinking agent to the folded part of the biosensor or to the folded part and around it, then heating the thermal-shrinking agent to semi-cure it.
Preferably, the coating is uniformly effected on the outer surface of the folded part or on that of the folded part and around it.
In this case, the above-mentioned thermosetting resin or photocurable resin is applied to the folded part or to the folded part and around it, and the resin thus having adhered to the folded part is heated or irradiated with light to cure it in the same manner as above.
In another case, the above-mentioned thermal-shrinking agent is applied to the folded part or to the folded part and around it, and the thermal-shrinking agent thus having adhered to the folded part is heated to semi-cure it in the same manner as above. The thermal-curing agent includes, for example, polyolefin, fluororesin and polyethylene.
In the manner as above, the warping and deformation of the substrate or the cover, which may start from the folded part, may be prevented.
<Fixation Tool>
For fixation with a fixation tool, for example, employable is a mode of pinching, encapsulating, capping, clamping with an elastic member, working with a thermal-shrinking agent, or fitting of an adhesive tape.
Pinching means a method of using a pinching and fixing tool such as a clip for pinching and fixing at least a part of the biosensor.
Encapsulation means a method of using a shaped fixation tool for encapsulating and fixing at least a part of the biosensor.
For capping, it is desirable that a cap is fitted to the end of the folded part of the biosensor. The material of the cap is preferably any of the following elastic member, thermal photo-curing agent, photo-curing agent or thermal-shrinking agent.
For clamping with an elastic member, for example, the elastic member may be natural rubber, synthetic rubber (e.g., butyl rubber) or silicone.
The thermal-shrinking agent includes, for example, polyolefin, fluororesin, polyethylene.
For carrying out the above-mentioned fixation method, for example, it is more desirable that an adhesive such as an acrylic adhesive is applied to the inside of the fixation tool (e.g., the part to be in contact with the inside part of the sensor, such as the elastic member or thermal-shrinking agent). With that, the fixation may be more ensured, and warping or deformation of the substrate or the cover may be prevented more surely.
The adhesive tape includes cellophane tape, polypropylene tape, acetate tape, Kapton (polyimide) tape, metal tape (e.g., aluminium, copper), paper tape, nonwoven fabric tape. As an adhesive for these tapes, generally preferred is an acrylic resin.
According to the fixation method as above, the biosensor of the invention may have a fixation tool for preventing the substrate and the cover thereof from being warped and deformed.
As is obvious from the above-mentioned description, a biosensor can be produced by folding or bending or folding and bending a sheet of an electrically-insulating flat substrate according to the invention, and the method is good in point of its producibility and economic aspect and from the viewpoint of a reduced environmental load to it. In using the biosensor of the invention for measurement, a sample fluid may be quantitatively introduced into the structure of the biosensor by utilizing capillarity, and the biosensor enables accurate measurement. Accordingly, a biosensor having good reproducibility can be realized according to a simple production method.
The method for producing the biosensor of the invention comprises folding and bending a sheet of a plate member, and it gives the intended biosensor in an extremely simple manner. In addition, when the production method is combined with a step of fixing the folded and bent plate member, then the biosensor thus produced is prevented from being warped or deformed.
When the method for producing the biosensor of the invention is combined with a step of cutting the folded and bent plate member, then the biosensor thus produced is also prevented from being warped or deformed.
Embodiments of the invention are described below with reference to the drawings.
A pattern 4 including an electrode is formed on the surface of the substrate part 1a of the plate member 1. Regarding the electrode pattern 4, the lower end thereof in the drawing is folded and bent like an L-form, and the L-shaped part perpendicularly crosses the reagent transfer path 8 that will be mentioned below. If desired, a reagent layer 11 may be provided in the L-shaped part of the electrode pattern 4.
On the other hand, an adhesive layer 10 is provided on the surface of the cover part 1b. The adhesive layer 10 has a role for sticking and fixing the folded substrate part 1a and the cover part 1b and additionally another role of defining the sample transfer path 8. Accordingly, the adhesive layer 10 is provided on both sides of the cover part 1b except the center part that is to be the sample transfer path 8. At the position at which the sample transfer path 8 crosses the perforations 9, formed is a sample inlet port 7 for injecting a sample 6 into the sample transfer path 8. In that manner, after the electrode 4, the adhesive layer 10 for defining the sample transfer path 8, and further the sample inlet port 7 have been formed on the plate member 1, then the plate member 1 is folded and bent along the perforations 9, whereby a biosensor is produced as in
When the biosensor is used for detection, then the sample inlet port 8 formed at the lower end thereof is kept in contact with a sample 6 so as to suck up the sample 6. The thus-sucked up sample 6 is brought into contact with the reagent layer 11 while passing through the sample transfer path 8, and the reagent reacts with the intended component in the sample. The electrochemical change of potential, current or the like caused by the reaction is detected with the electrode. When the reagent layer is not in the sensor, then the intended component is detected only by the electrode.
Having the constitution as above, the biosensor can be produced in a process of one-time folding, and therefore it does not require any complicated positioning that is indispensable in lamination in producing conventional sensors. The advantages of the biosensor of the invention are that the production process may be simplified and the producibility of the products may be increased.
Other embodiments of a folded biosensor are shown in FIGS. 3 to 16. In
It is not always necessary to provide the sample inlet port at the end of the upper and lower parts or the side face, like
The configuration of the substrate part and the cover part in the plate member is not limited to upper and lower positions as in FIGS. 2(a), 3 and 4, but may be left and right positions as in
The above-mentioned electrodes may be disposed on the side of the cover part 1b, not limited to the side of the substrate part 1a of the plate member 1. Further, as in
Other examples of the facing electrode structures are shown in
Regarding the electrodes therein, two electrodes, or that is, a working electrode and a counter electrode form the sensor unit in the above-mentioned examples. However, the electrodes of forming a sensor unit are not limited to two, but three electrodes, or that is, a working electrode, a counter electrode and a reference electrode may form a sensor unit. Examples comprising such three electrodes are shown in
Preferred examples where the plate member 1 has perforations are mentioned above. However, the constitution of facilitating the folding and bending working herein is not limited to perforations, but as in
As in
The present biosensor is not limited to the above-mentioned, folded laminate structures, but may be a cylindrical structure constructed by bending a sheet of a plate member. One typical constitutional example is shown in
In the above-mentioned drawings, a reagent layer is not always shown, but in the drawings where it is not shown, a reagent layer may be provided, if desired. For example, when a nickel electrode is used, then the sensor may be used as a protein sensor (U.S. Pat. No. 5,653,864) for protein detection even though it has not a reagent layer. When a platinum electrode is used, then the sensor may be used as a conductivity sensor or a hydrogen peroxide sensor; and when further combined with an oxygen-permeable membrane and an electrode, then it may be used as an oxygen sensor. On the other hand, when a reagent layer is used, then various types of biosensor may be produced, for example, blood sugar sensors, urine sugar sensors, glycosylating hemoglobin sensors (JP-A-2001-204494), lactate sensors, urate sensors, cholesterol sensors, alcohol sensors, glutamate sensors and pyruvate sensors of using enzyme and mediator; pH sensor of using silver/silver chloride electrode, quinhydrone and inorganic salt; a pH sensor and a DNA primer; single nucleotide polymorphisms sensors of using a DNA polymerase; and DNA chips of using a immobilized nucleic acid probe, and these may be applied to various sensors of detecting various chemical and physical conditions. The reagent layer may be formed on or around an electrode through which a sample transfer path passes.
Around a sample inlet port and on the surface of a sample transfer path, a surfactant and a lipid may be applied for easy introduction of a sample.
The materials, the production methods and the applications of the above-mentioned embodiments are described in detail hereinunder.
As the plate member, usable are plastics such as polyethylene terephthalate, biodegradable materials such as polylactic acid, and paper.
The electrode material usable in the present sensors include metals such as platinum, gold, silver/silver chloride, silver copper, palladium, iridium, lead, nickel, titanium, tin oxide, platinum black. These have good conductivity, and may be formed according to vapor deposition, sputtering, plating, CVD, or coating and drying. Though inferior to platinum and gold in point of the conductivity thereof, carbon powder may readily form an electrode according to a screen-printing method by making it into a paste followed by applying it to a substrate, like silver powder. In addition, a particulate substance of platinum or gold may be formed into a paste and may be worked by printing.
As a carbon material, also usable are carbon nanotubes, carbon microcoils, carbon nanohorns, fullerenes, dendrimers and their derivatives. These are suitable for fixation of molecule identification elements or for electrode materials because of their peculiar characteristics (structure, conductivity).
In a protein sensor, nickel is preferred for the electrode material. Nickel may oxidize the amino group of protein under a predetermined condition and may be a protein sensor. It may be usable for FIA (flow injection analysis).
Preferably, the adhesive layer is formed according to a screen-printing process. An adhesive double-coated tape may also be used for it. The adhesive usable herein includes, for example, a bond, a sticky paste.
A reagent may be added to the adhesive layer, and an adhesive layer and a reagent layer may be formed at a time according to a screen-printing process.
Preferably, the reagent layer is formed according to a method comprising dropping a reagent in the form of an aqueous solution thereof through a dispenser and drying it. By controlling the viscosity thereof, the reagent layer may also be formed according to a screen-printing process.
When the sensor has one reagent layer, then it may detect one substance. However, when two different types of substances are detected, then different types of reagent layers may e formed on a sheet of an electrically-insulating flat substrate (JP-A-1-291153), as in FIGS. 19 to 21. In this case, a projection (12) may be formed of carbon, resist or water-absorbing material according to a screen-printing method in the intermediate space between the reagent layers for preventing the reagent layers from being mixed together, as in the drawings. In this case, the initial thickness of the projection must be lower than that of the adhesive layer, and when folded and bent, the top and the left and right sides of the projection must not be in contact with any others. This is for promoting the running of a sample through the sensor structure. When a water-absorbing substance is used, then it swells after a sample has passed through it, and it functions to prevent the dissolved reagents from being mixed together. When the number of the electrodes is not 4 (FIGS. 19 to 21, (a), (b)) but is 3, then, for example, one center electrode may be used as a common counter electrode (FIGS. 19 to 21, (c), (d)).
The bonding of the reagent to the electrode surface or to the substrate may be carried out according to an adsorption method or a covalent-bonding method after drying.
For the reagent, herein usable are enzyme, antibody, nucleic acid, primer, peptide nucleic acid, nucleic acid probe, microorganism, organelle, receptor, cell tissue, molecule identification element such as crown ether, mediator, intercalator, coenzyme, labeled antibody substance, substrate, inorganic salt, surfactant, lipid.
For example, in an enzyme sensor, the type of the enzyme serving as a molecule identification element is varied depending on the subject to be detected. For example, when the subject to be detected is blood sugar (glucose) or urine sugar, then glucose oxidase or glucose dehydrogenase is used; when the subject to be detected is glycosylating hemoglobin, then a mixture of fructosylamine oxidase and protease is used; when the subject to be detected is lactate, then lactate oxidase is used; when the subject to be detected is total cholesterol, then a mixture of cholesterol esterase and cholesterol oxidase is used; when the subject to be detected is urate, then urate oxidase is used; when the subject to be detected is ethanol, then alcohol oxidase is used; when the subject to be detected is glutamate, then glutamate oxidase is used; when the subject to be detected is pyruvate, then pyruvate oxidase is used.
In the above-mentioned enzyme sensors, an electron transmitter (mediator) is used along with enzyme. For the mediator, herein usable are potassium ferricyanide, ferrocene, ferrocene derivatives, nicotinamide derivatives, flavin derivatives, benzoquinone and quinone derivatives.
In a pH sensor, a reagent layer of an inorganic salt such as sodium chloride or potassium chloride and quinhydrone is formed on a substrate with a silver/silver chloride electrode and any other electrode formed thereon. In this case, the electrode-to-electrode potential change is measured.
In a single nucleotide polymorphisms (SNPs) sensor (A. Ahmadian et al., Biotechniques, 32, 748, 2002), a mixture of primer, DNA polymerase and deoxyribonucleotide triphosphate is additionally used as a reagent on the above-mentioned pH sensor. In this, when the subject DNA to be detected in a sample is complementary to the primer, then the pH change is measured.
In an immune sensor, an antigen-antibody reaction is utilized, and for example, when human serum albumin is measured, then an anti-albumin antibody is used as a molecule identification element therein. In the immune sensor, the electrode-to-electrode potential that varies by formation of an antigen-antibody complex shall be measured.
In a microorganisms sensor, microorganisms such as, for example, those of Pseudomonas fluorescence (subject to be detected: glucose) or Trichosporon brassicae (subject to be detected: ethanol) are used as a molecule identification element. These microorganisms are of oxygen respiration (aerobic), or produce a metabolite in the absence of oxygen, and the sensor with them is to electrically detect the oxygen respiration amount or the metabolite amount.
In an organelle sensor, used is a cell organelle as a molecule identification element. For example, when a mitochondrial electron transmitter granules are used, then NADH can be measured. This principle is as follows: NADH is oxidized by mitochondrial electron transmitter granules, whereupon this consumes oxygen, and on the basis of the oxygen amount in this stage as an index, NADH or NADPH may be measured.
In a receptor sensor, used is a rector of, for example, cell membrane as a molecule identification element. The object to be detected may be hormone or neurotransmitter. The detection principle is as follows: The receptor change is converted into a potential, and this is measured through the electrode in the sensor.
In a tissue sensor, used is an animal or plant tissue as a molecule identification element. For the animal or plant tissue, for example, herein usable is a frog skin, an animal liver section, or a cucumber or banana peel. The measurement principle is as follows: For example, in a sodium sensor using a frog skin tissue, the frog skin tissue selectively penetrates sodium ions, whereupon the potential of the skin tissue varies. Accordingly, the potential change is measured to determine the amount of sodium ions.
another example of the applications of the biosensors described herein is a DNA chip (JP-A-5-199898). On an electrode array (U.S. Pat. No. 4,225,410) as in
Preferably, the biosensor of the invention is stored in dry. Preferably, it is stored together with a desiccant. The desiccant includes active alumina, zeolite, silica gel, calcium chloride.
When the above-mentioned biosensor is used for measurement, then the biosensor is fitted to an apparatus, and the electric value generated in the biosensor is measured. For this measurement, the apparatus is provided with a measuring unit of measuring the electric value of the biosensor and a display unit of displaying the measured value. For the measuring method at the measuring unit, employable is any of potential step chronoamperometry, coulometry or cyclic voltammetry. The apparatus may comprise a memory unit for storing the measured values. In addition, it may have a wireless unit such as a bluetooth mounted therein for remote control of the measured values.
The folded part 105 is formed when the plate member is shaped into the sensor by folding and bending it, for example, along the perforations formed through the substrate.
The mold 106 does not always require a groove, but it may be a mold (heat source) having a flat surface. The edge of the folded part of the biosensor (“edge of the folded part” means a part except the area around the sample inlet port 104 and the reaction detector part, and this indicates the edge region where the folded part of the biosensor exists, including the folded part 105 or the folded part 105 and around it) may not be in direct contact with the mold, and the edge of the folded part may be modified by the heat from the mold.
In this, since enzyme may be deactivated by heat, it is desirable that the region to be heated is limited to the folded part 105 of the biosensor 101, or the folded part thereof and around it, or around the edge part of the cover on the opposite side of the folded part (cover edge—“cover edge” is a part except the area around the sample inlet port 104 and the reaction detector part, indicating the region where the cover edge on the opposite side of the folded part exists) Accordingly, the sample inlet port and the reaction detector part may be so controlled that they are hardly influenced by the heating.
Like in the above, it is desirable that the heating coils are disposed in the area where the enzyme inside the biosensor 101 is not influenced by the heat from them.
In
Like in the above, the molds are preferably so disposed that the enzyme inside the biosensor 101 is not influenced by their heat.
In
Like in the above, the molds are preferably so disposed that the enzyme inside the biosensor 101 is not influenced by their heat.
When the chemical reagent in
When the chemical reagent in
The invention is described in detail with reference to the following Examples, to which, however, the invention should not be limited. In the Examples, a glucose biosensor is used as an example of an enzyme sensor.
In the present sensor, a sample is introduced into it through its sample inlet port by capillarity. Thus introduced, the glucose solution acts as follows: By the oxidation of glucose, ferricyanide ion is converted into ferrocyanide ion owing to the catalyst action of GOD in the reagent layer, as in the following formula 1:
GOD
Glucose+Ferricyanide Ion→Gluconolactone+Ferricyanide Ion [Formula 1]
The produced ferrocyanide ion is oxidized according to the electrode reaction of the following formula 2, on a carbon electrode, and is thereby electrochemically detected.
Electrode
Ferrocyanide Ion→Ferricyanide Ion+e− [Formula 2]
According to the detection method of using the glucose sensor of the invention, the produced ferrocyanide ion is oxidized by an anode electrode to give an anode current, and the ferrocyanide ion is again returned to ferricyanide ion. As in the above, by detecting the current value change of the concentration of the ferrocyanide ion produced by the enzyme reaction, it is possible to quantitatively determine the glucose.
Next described are a production method and a measurement method.
PET having a length of 65 mm, a width of 6 mm and a thickness of 188 μm is used as a sensor substrate. On the sensor substrate, formed were two carbon electrodes at an interval of 2.6 mm, each having a width of 1.3 mm, by the use of a screen-printing device. An adhesive was applied to it to form an adhesive layer on the substrate according to a screen-printing process. Perforations were formed at the part to be folded. The sample amount was 0.5 μl.
A reagent layer of enzyme and mediator was formed as follows: Glucose oxidase (GOD) and potassium ferricyanide (mediator) were dissolved in distilled water, and applied on the surface of the electrodes. 4 units of GOD and 0.1 mg of potassium ferricyanide were dissolved in 10 μl of distilled water. 3 μl of the GOD solution was applied onto the electrode surface and dried in vacuum to form an enzyme/mediator reagent layer on the two electrodes.
An example of measuring blood sugar (blood glucose) by the use of the glucose sensor is described. As sample solutions to be assayed for detection of blood sugar by the use of the present glucose sensor, used were whole blood samples specifically so prepared as to have a glucose concentration of 50, 100, 200, 300, 400 or 500 mg/dl and a hematocrit value of 40%. The measurement was attained through potential step chronoamperometry. 0.5 μl of the blood sample was led into the sensor through the sample inlet port by capillarity, and after 5 seconds, a potential of 900 mV was applied to the two electrodes in the sensor. Further after 5 seconds, the current value running through the sensor was measured.
In Example 1, a reagent layer of glucose oxidase and potassium ferricyanide was formed on the electrodes. In Example 2, it was formed not on the electrodes but on the cover part. This is described with reference to
| Number | Date | Country | Kind |
|---|---|---|---|
| 2003-280261 | Jul 2003 | JP | national |
| 2004-012076 | Jan 2004 | JP | national |
| 2004-060834 | Mar 2004 | JP | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/JP04/05436 | 4/15/2004 | WO | 1/25/2006 |
