JP2003503702A - General purpose transducer - Google Patents

Abstract

(57) Abstract: The present invention relates to a general-purpose transducer based on the miniature general-purpose transducer as described above, which is used for measuring a substance concentration or an ion activity in a fluid, for example, in analytical chemistry or medical diagnostics. The present invention relates to a chemical sensor and a biosensor. The universal transducer according to the invention has a carrier consisting of at least two flat carrier layers (1, 2), each carrier layer (1, 2) having at least one perforation (4, 5). These perforations (4,5) form coherent cavities extending from the first active surface of the carrier and beyond the first and second carrier layers. The conductive layer in contact with the filling material of the cavity is at least partially arranged on the surface of at least one of the two carrier layers (1, 2), with the surface facing away from the first active surface (10). It is arranged so that it becomes.

Description

Detailed Description of the Invention

[0001]

TECHNICAL FIELD OF THE INVENTION

The present invention relates to general purpose transducers and chemical and biosensors based on miniaturized general purpose transducers. Sensors of this type are used, for example, in chemical analysis or in medical diagnostics for the determination of substance concentration or ionic activity in fluids.

[0002]

[Prior art]

In the prior art, chemical and biosensor elements are fabricated on the basis of a carrier with a metal contact specified for each analyte and a membrane or gel material. In this case, the potential difference on the ion selective electrode is
With these elements it is measured relative to a reference electrode according to the potentiometric titration principle. Amperometric sensors measure the current between a working electrode and a reference or counter electrode after application of a voltage based on the two-pole or three-pole principle (Frie.
See drich Oehme, Chemische Sensoren, Vieweg Verlag 1991).

In P 41 15 414, very miniaturized chemical and biosensors are known. In this case, the cavities are integrated in a carrier made of a semiconductor material such as silicon. These cavities are coated on their inner surface with a metal film and contain a membrane or gel material that detects substances.

However, a disadvantage of these prior art is that the carrier for such a sensor is, for example, amperometrically determined, when the metal film is photolithographically configured over a large area of the three-dimensional surface of the cavity. For that reason, only two kinds of metal films can be provided. Even if the conductive layer should not be in direct contact with the measuring medium, the inner surface of the cavity may be photolithographically configured in the contacting region with the measuring medium so that any metal film may be applied in this contacting region. There is no such thing. However, this type of three-dimensional photolithographic structure represents a great deal of technical difficulty and cost.

Another disadvantage of the prior art is that the known sensor elements have heretofore made it impossible to operate the amperometric and potentiometric sensor elements together on a single carrier. It was there. That is, in the conventional technology,
Both the amperometric measurement sensor and the potentiometric measurement sensor element are in contact with the same measurement medium, and the current of the amperometric measurement sensor flows through the contact surface between the membrane and the measurement medium. At that time, the potential difference measurement of the adjacent potentiometric titration measurement sensor is disturbed.

[0006]

[Problems to be Solved by the Invention]

Therefore, an object of the present invention is to provide a general-purpose transducer that is easy to manufacture and that can realize a three-dimensional structure of a transducer by using a simple means. The universal transducer should also be suitable for using amperometric and potentiometric sensors for measuring the same fluid at the same time.

[0007]

[Means for Solving the Problems]

This problem is solved by a universal transducer according to claim 1 and a method of using this universal transducer according to claim 27. Preferred embodiments of the universal transducer according to the invention and the method of use according to the invention are set forth in the dependent claims.

According to the invention, a universal transducer comprises a carrier with at least two flat carrier layers. Cavities may be formed by perforations through these carrier layers and contact the analyte on one side of the carrier. The surface of the carrier layer opposite the contact surface is provided with a conductive layer or a conductive film that functions as an electrode. The cavity is itself filled with a fill, which may include a substance detection membrane such as an ion selective membrane and / or a gel. Therefore, according to the present invention, individual carrier layers and electrodes can be sequentially assembled, and a structure that eliminates the three-dimensional photolithographic structure is realized.
Thereby, for example, the transducer is manufactured without a special photolithographic structure and the electrodes of the transducer do not come into contact with the measuring medium. Whereas the carrier layer forming the first active surface does not have a conductive layer, when the transducer has a single conductive layer, the conductive layer is located on one of the carrier layers at a considerable distance from the first active surface. . This makes it possible to easily avoid contact between the conductive layer and the measuring medium. In essence, in contrast to the prior art, it is possible to arrange the electrodes three-dimensionally within the depression of a universal transducer. Further, for example, in order to simultaneously realize a plurality of amperometric measurement sensors or a plurality of potentiometric measurement sensors, or, for example, an amperometric measurement sensor or a potentiometric measurement sensor on the same carrier, simultaneously for the same measurement medium Moreover, it is further possible to provide multiple cavities in the same carrier as a universal transducer.

In this case, the difference between the potentiometric measurement sensor element and the amperometric measurement sensor element is that in this case, for example, as in the case of sputtering using a shadow mask, it is only necessary to select a location and apply it to the electrode film. is there.

In particular, the construction of most different amperometric and potentiometric sensors for analytes is realized in particular on the same principle, but different sensor elements can be manufactured simultaneously. The carrier layers for the different sensor elements differ thereby only in the arrangement of the perforations in the individual carrier layers. Electrode layers and fillings can also be applied at selected locations, for example by applying different substance detection materials in the cavities in the area of the perforations each time, so that a vertical structure of each sensor element is realized. To be done.

By this method, a general-purpose transducer can be manufactured, and a multi-sensor having different types of sensor elements can be newly formed for this general-purpose transducer.

The carrier layer of the universal transducer according to the invention is preferably vinyl fluoride resin, polyethylene, polyoxymethylene, polycarbonate, ethylene / propylene copolymer COP, polyvinylidene chloride, polychlorotrifluoroethylene,
Polyvinyl butyral, cellulose acetate, polypropylene, polymethylmethacrylate, polyamide, tetrafluoroethylene / hexafluoropropylene copolymer COP, polytetrafluoroethylene, phenol formaldehyde, epoxide, polyurethane, polyester, silicone, melamine formaldehyde, urea formaldehyde, aniline formaldehyde , Kapton, etc. or synthetic material such as silicon, ceramic or glass. Thus, the universal transducer according to the invention can be realized based on various production techniques, such as synthetic material injection molding technology, synthetic material foil technology, ceramic technology, silicon technology.

The conductive layer may be formed from a metal, in particular a noble metal such as platinum, gold, silver, or an alloy, or a screen printing paste based on eg graphite or a metallic material.

The filling is preferably formed by known methods from known materials for ion-selective membranes, for example polyvinyl chloride PVC, silicone, polyurethane and the like. For gel filling, for example, gelatin or polyvinyl alcohol is used.

The encapsulating material may preferably consist of a material that is compatible with a material such as a membrane or gel, such as an epoxide resin.

Vinyl fluoride resin, polyethylene, polyoxymethylene, polycarbonate, ethylene / propylene copolymer COP, polyvinylidene chloride, polychlorotrifluoroethylene, polyvinyl butyral, cellulose acetate, polypropylene, polymethyl methacrylate, polyamide, tetrafluoro Ethylene / hexafluoropropylene copolymer COP, polytetrafluoroethylene, phenol formaldehyde, epoxide, polyurethane, polyester, silicone, melamine formaldehyde, urea formaldehyde, silicone, aniline formaldehyde, Kapton, etc., mainly in the range of 1 μm to several micrometers. The very thin material in the region of the first active surface covers the diameter measurement window, for example gas permeability. Rather it is used for other membranes such as sexual membrane. Such a membrane is preferably applied to the first active surface of the first carrier layer,
Alternatively, it is transferred from the liquid phase.

The thickness of each carrier layer is several μm to several mm, preferably 100 μm or less. The opening of the perforation (measurement window) in the first carrier layer on the first active surface is preferably several μm to several mm, preferably several tens to several hundreds μm. The thickness of the conductive layer applied as an electrode on each surface of the carrier layer opposite to the first active surface is within several μm.

According to a preferred embodiment, the flow channels are provided with channel carriers and channel covers which supply analytes and liquids to the individual measurement windows, for convenience.
Rather, it is formed from the same material as each carrier layer. The thickness of the channel carrier and the channel cover is in this case a few μm to a few mm, preferably 10 μm.
It is 0 μm.

Depending on the choice of material, the shaping of the carrier layer can be done by various methods. If the carrier layer is made of silicon, for example, the formation of perforations is done by the method of strong corrosion. A corrosive medium such as potassium hydroxide KOH or a dry etching method is used here. In this case, perforations of various cross-sections, for example square, rectangular and circular, are formed. In anisotropic etching, for example, in the direction toward the first active surface, perforations are formed in a pyramid shape that gradually become thinner from one surface of the carrier layer toward the other surface.

When a plastic material is used for the carrier layer, the carrier layer is formed by injection molding. At that time, perforation is generated by the molding of the injection molding tool. However, it is also possible to use a flat carrier material, such as a sheet of plastic material for each carrier layer with perforations, by cutting, boring, embossing, etching.

The conductive layer is applied to the carrier layer using known thin film technology methods such as vacuum deposition or sputtering. This structure occurs in evaporation or sputtering with a shadow mask. Here you can also use photoengraving,
In this case, in manufacturing the transducer according to the invention, in no case should three-dimensional structures be provided in the depressions. The conductor electrode can also be formed by screen printing or electrolytic separation.

The filling of the perforations, eg of membrane or gel, is preferably introduced into the cavity using an automatic compounding device. This method is suitable for application of capsule filling material applied by screen printing.

In order to manufacture a transducer according to the invention, firstly a carrier layer is provided with perforations and a conductive layer is applied, respectively, as required. A conductive layer may also be applied before the perforations are formed. The carrier layers and, if appropriate, the channel carriers and the channel covers are then stacked on top of one another and bonded to one another. For such bonding, various materials and methods are used depending on the material of the carrier layer, channel carrier and channel cover. If the carrier layer and the channel carrier / channel cover are made of a silicon material, known bonding methods, for example anodic bonding, are used for bonding the individual films. In addition, the bonding of the carrier layers can be done using adhesive technology. For carrier layer,
When used for the channel carrier and the channel cover, the film can be similarly applied. If a foil material is used, it is also possible to combine the various layers as a film by a lamination method such as thermal lamination or by known welding methods.

According to the present invention, a general-purpose transducer having a simple structure and capable of performing various measurement methods (amperometric titration measurement, potentiometric titration measurement) with the same measurement solution on the same carrier is provided. This carrier is characterized in that it has a structure in the depression. First of all, the individual carrier layers are formed and perforated and then the conductive layer is formed, or alternatively, the conductive layer is first formed and then the perforated and then the individual carrier layers are stacked. Layered structure in which the individual perforations form a vertically continuous cavity, after which the cavity is filled with a suitable packing, for example a substance detection membrane or gel. Therefore, a general-purpose transducer having a three-dimensional structure of this type according to the present invention can be easily manufactured.

Coupling means, for example chromium, are applied between the carrier layer and the conductive layer. Non-interfering films such as cellulose acetate and polyurethane (Antiinterferenz
Another film, such as a schichten) is applied between the conductive layer and the filling in the perforations.

[0026]

DETAILED DESCRIPTION OF THE INVENTION

Hereinafter, preferred embodiments of the present invention will be described. In the following embodiments and drawings, the same components are designated by the same reference numerals. In one described universal transducer, multiple sensors (eg, I, II, III in FIG. 1) are used.
, IV, V) are described by the same element with respect to type or function (eg packing 9), the numbers for the same elements in type or function are:
The Roman numeral (by the number after the period (eg 9.1, 9.2, ... 9.5))
Assigned to the sensor element specified by IV).

FIG. 1 shows a carrier composed of a first carrier layer 1, a second carrier layer 2 and a third carrier layer 3, all fixed to one another. The carrier layers 1 to 3 are configured to use the perforations 4 to 6 and the conductive layers 7 and 8 to generate various sensor elements I to V in the area of the perforations. The carrier layer 1 has perforations 4 (4.1 for sensor element I, 4.2 for sensor element II, and so on) and the carrier layer 2 has perforations 5 (5.1-5.5). , Carrier layer 3
There is a perforation 6 (6.1-6.5). The perforations in the carrier layers 1 to 3 are located so as to create cavities extending into the three carrier layers.

A conductive layer 7 is partially coated on the surface of the carrier layer 1, and another conductive layer 8 is coated on the surface of the carrier layer 2. The perforations 4 to 6 are used as cavities for intake of the filling 9 (membrane material or gel material). After the filling 9 has been supplied, the cavity is closed using the capsule filling material 11. In the perforation of the first carrier layer, an effective sensor surface 10 is produced in each case in the phase boundary outside the filling 9.

In the first carrier layer a platinum film 7 is realized and in the second carrier layer a silver film is realized as a conductive layer. A wide variety of sensor elements can be realized by such a general-purpose transducer.

Element I represents a reference electrode for another sensor element. The silver film 8.1 can be salified for the filling 9 at the contact surface. Here as filling 9.1,
For example, potassium chloride KCl solution is gelatin or polyvinyl alcohol (PV
A) is fed from above. Such an element is a conventional silver Ag / silver chloride AgCl
It corresponds to the reference electrode. Such a reference electrode is, for example, an ion selective electrode (ISE).
) Used together.

Such an ion selective electrode (ISE) is realized as the sensor element II. The sensor element II has the same structure as the element I. However, here the cavity is filled with an ion-selective membrane 9.2 in the region of the perforations 4.2, 5.2, 6.2. The ion-selective membrane is composed of, for example, polyvinyl chloride PVC material or silicone containing an ionophore as an electroactive substance along with a softening agent and an additive. The polyvinyl chloride PVC membrane 9.2 is in direct contact with the metal film 8.2 (Ag). When the liquid measurement medium interacts with the ion-selective membrane 9.2 in the region of the measurement window 10.2, it may be measured in the region of the measurement window in contact with the measurement medium in the region of the measurement window 10.1. The potential difference with respect to the reference electrode I is configured to be possible.

Element III represents another potentiometric sensor element used for urea calculation. Here, the ion-selective membrane 9.3 is first supplied from the perforations 4.3 of the carrier layer 1 or the perforations 6.3 of the carrier layer 2 to the cavities in the region of the perforations 5.3 and 6.3 for the calculation of ammonium. It Such ion-selective membranes are likewise produced for polyvinyl chloride PVC materials with softeners and additives and for ammonium with ionophores. Then, the second membrane 9 containing, for example, polycarbamoyl sulfonate gel containing the enzyme urease as a biological component.
． 3.1 is supplied to the membrane 9.3. When measuring, the liquid measuring medium in the urea analysis interacts with the membrane 9.3.1 in the region of the measuring window 10.3. The urea molecule is catalyzed by the enzyme urease. Membrane 9.
The ammonium concentration changed in 3.1 now detects the ion-selective ammonium membrane 9.3. The measurement is performed on the reference electrode I. Therefore, the potential of the urea sensor in the silver film 8.3 decreases. The metal film 8.3 extends perpendicularly to the focal plane and is sequentially exposed to the metal film 8.5 of the sensor element V. At this time, the connection is made electrically.

The glucose sensor is realized as sensor element IV. Perforation 4.4, 5.4
, The cavity in the region of 6.4 is then the enzyme glucose oxidase (GOD)
Filled with polyvinyl alcohol containing. When glucose in the measuring medium interacts with the membrane material 9.4 in the region of the measuring window 10.4,
Glucose catalyzes using the enzyme GOD. At this time, hydrogen peroxide H2O2
Occurs. This hydrogen peroxide H ₂ O ₂ acts electrochemically at the platinum electrode 7.4 by amperometric titration. This occurs on the basis of the measuring principle with amperometric titration, which leads to a platinum electrode 7.4 and a silver Ag / silver chloride AgCl electrode 8.4 at the current.
Is measured between. Measurements are made using the bipolar arrangement by the method previously described.

When the measurement has to be carried out simultaneously with potentiometric sensor elements (for example sensor elements II and III), a particular advantage, based on the geometry of the universal transducer, is to make a three-pole measurement. In this case, the potential of the platinum working electrode 7.4 is calculated using the reference electrode I. The current of the sensor element IV flows through the silver Ag / silver chloride AgCl counter electrode 8.4.

The working electrode and the counter electrode are arranged vertically in the cavity according to the invention, while the reference electrode I contacts the measurement medium outside the cavity of the sensor element IV via the measurement window 10.1, while the current is measured. Since it flows through the measuring medium rather than the window 10.4, the measurement at the sensor element by potentiometric titration is not disturbed.

The sensor element V sequentially calculates the dissolved oxygen concentration in the liquid measurement medium for the glucose sensor IV. The cavities in the area of perforations 4.5, 5.5, 6.5 are now filled with potassium chloride KCl solution as well as potassium chloride KCl gel. The perforations 4.5 in the carrier layer 1 are covered with a gas-permeable membrane 13. Dissolved oxygen in the liquid measuring medium diffuses through the gas-permeable membrane and electrochemically acts on the platinum electrode 7.5 based on the amperometric measurement principle. Therefore, platinum electrode 7.5 and silver Ag / silver chloride AgCl electrode 8.5
Is measured after pressurization with a voltage of several hundred mV in current between and.

FIG. 2 a) shows the sensor element IV of FIG. Another shape of the perforations 4 in the carrier layer 1 is shown in Figure 2b). Here, the conductive layer 7 extends to the area of the perforations. At this time, it is possible to apply the conductive layer 7 to the conductive layer 7 by, for example, vacuum deposition or sputtering after the perforations are generated. FIG. 2c) shows a similar embodiment. However, here the conductive layer 7 does not extend to the region of the inner surface of the perforations 4.
All three sensor elements are suitable for amperometric measurements. The filling material 9 is a membrane material or a gel material depending on the shape of the sensor element, and also contains various biological components that are common in biosensor technology. Enzymes, microorganisms and antibodies fall into this category.

The example of the metal film 7 in the carrier layer 1 makes it possible to create a transducer structure, in which the film 7 extends up to the measuring window 10 depending on the shape of the sensor element.

FIG. 3 shows various examples of transducers, such as an ion-selective electrode according to Example II in FIG. 1 and a reference electrode according to Example I in FIG. Regarding the perforations in the carrier layer 1 of FIG. 2, the perforations in the carrier layer 2 will be described in detail in the examples one by one. At this time, the conductive layer 8 extends to the carrier layer 1 (FIGS. 3a) and b)), respectively. In FIG. 3c), the conductive layer 8 lies only on the flat side of the carrier layer 2.

The embodiment of the metal film 8 in the carrier layer 2 makes it possible to create a transducer structure, in which the size of the film 8 varies with respect to the carrier layer 1 and the measuring window 10.

When a reference electrode is realized based on the device I of FIG. 1, the conductive layer 8 in FIGS. 3a) to 3c) is composed of, for example, a silver chloride film. The cavity filling 9 in the carrier layers 1 to 3 is then also composed of potassium chloride KCl gel. On the basis of the structure according to FIG. 3, it is also possible to form the ion-selective electrode with a polymer film. Therefore, the conductive layer 8 is made of, for example, silver. Perforations 4, 5,
The cavity filling 9 in the region of 6 in the example of FIGS. 3a) and b) is made of, for example, polyvinyl chloride PVC, silicone, or other material of the ion-selective film and is equipped with associated active ingredients. .

In FIG. 3c) an ion selective electrode fitted with an internal electrolyte is shown. Perforation 4
The cavities in the areas 5 and 5 are for the moment filled with an ion-selective membrane 9.1. The membrane itself does not contact the conductive layer. Potassium chloride KCl gel 9 is applied on the ion selective membrane. This potassium chloride KCl gel 9
Are in direct contact with the silver chloride film 8.

In the embodiment of FIG. 4, an additional membrane 13 is additionally provided for each sensor element. FIG. 4a) shows a glucose sensor element in which the measuring window 10 is closed, for example by means of a polyurethane (PU) membrane. This polyurethane membrane is fixed to the carrier layer 1. Conductive layer 14 made of platinum
Are fixed to the membrane 13 and the carrier layer 2. The filling 9 is composed of polyvinyl alcohol together with the enzyme glucose oxidase (GOD), for example. The filler 9 is a reference electrode layer and a counter electrode layer 8 made of a silver chloride film.
Is in direct contact with

Similar to the glucose sensor according to FIG. 4a), an oxygen sensor element is realized.
Instead of the polyurethane (PU) membrane 13, a gas permeable membrane is
For example, it is made of Teflon (registered trademark) tower or silicon. The filling 9 in this case consists of a potassium chloride KCl solution as well as a potassium chloride KCl gel.

Another embodiment of the glucose sensor is shown in FIG. 4b). The difference from FIG. 4 a) is that the platinum working electrode 15 lies directly above the carrier layer 1. The membrane 13 is similarly made of polyurethane.

Another embodiment of the oxygen sensor is shown in FIG. 4c). In contrast to FIG. 4a), the platinum electrode layer 14 lies only below the carrier layer 2.

4a) and 4c) realize a sensor for measuring dissolved carbon dioxide concentration in a liquid measuring medium. Such sensors operate on the Sebelinghaus principle. The membrane 13 is then composed of a gas-permeable material. Filling 9
Is an electrolyte gel. The electrode layer 14 is composed of iridium oxide, which is a material sensitive to pH.

During measurement, carbon dioxide is diffused by the gas permeable membrane 13. With this membrane, the pH value in the electrolyte filling 9 is changed, and the membrane composed of the silver chloride film 8 can be measured with respect to the reference electrode by the pH-sensitive iridium oxide electrode 14.

FIG. 5 shows a carbon dioxide CO 2 sensor as another embodiment. At this time, the silver film 8 and the silver chloride film 14 are applied to the carrier layer 2. After the production of the transducer, the cavities in the region of the perforations 5 and 6 are composed of a pH-sensitive polymer membrane (eg polyvinyl chloride PVC), so that by binding with the silver film 8 the ion-selective electrode is for pH value. Is formed. The internal electrode layer 16 that is in contact with the surface of the silver chloride film 14 as well as the surface of the pH-sensitive membrane 9 is applied on the pH-sensitive membrane. A gas permeable membrane 13 made of, for example, silicon is injected into the internal electrode layer 16. The inner electrode layer also fills the reservoir 16A. This reservoir extends the life of the sensor.

The sensor is thus realized for the measurement of carbon dioxide CO ₂ concentration in an aqueous medium according to the Severinghaus principle. During measurement, carbon dioxide is diffused by the gas-permeable membrane 13. This membrane is composed of a silver chloride film 14 with respect to a reference electrode by an ion-selective electrode that changes the pH value in the electrolyte film 16 and is composed of the ion-selective membrane 9 and the silver film 8 and is pH-sensitive. Can be measured.

As an example other than this, FIG. 6 shows the sensor element again based on the example IV of FIG. Here, a channel 20 is additionally incorporated. Channel 2
The channel carrier 18 present in the 0 gap is applied to the carrier layer 1. The channel carrier 18 is sealed by a channel cover 19. In this way the channel 20 is realized with a very narrow cross section. With the same channel (eg
It is also possible to combine various sensor elements (shown in FIG.

An example in which the channel 20 is attached is shown in FIG. 7 as an extension of FIG. This example refers to FIG. Here, instead of the sensor elements I and V, there are pipes 21 and 22 for supplying a liquid measuring medium. The liquid measuring medium flows into the channel 20 which comprises the channel carrier 18 and the cover 19. In this example, the element II containing the filling 9.2 made of potassium chloride KCl gel can realize a reference electrode fitted with a silver chloride electrode 8.2. The sensor element in position III is a urea sensor, for example as in FIG. 1, whereas the glucose sensor is in position IV. The urea sensor III is measured based on the measuring method by potentiometric titration with respect to the reference electrode II. The glucose sensor IV is measured based on the triode principle. For this reason, the platinum electrode 7.4 is used as the working electrode. The reference electrode II is used for adjusting the polarization electromotive force of the working electrode 7.4, while the silver film 8.4 is used for the counter electrode of the current.

[Brief description of drawings]

[Figure 1]   It is a figure showing a general-purpose transducer provided with a plurality of sensor elements.

[Fig. 2]   It is a figure showing various glucose sensors.

[Figure 3]   It is the figure which showed various ion selective electrodes.

[Figure 4]   It is a figure showing various sensor elements.

FIG. 5 shows a carbon dioxide CO ₂ sensor according to the invention.

[Figure 6]   It is the figure which showed the glucose sensor for amperometric measurement provided with the flow channel.

FIG. 7 illustrates a universal transducer with multiple sensor elements and flow channels.

[Procedure for Amendment] Submission for translation of Article 34 Amendment of Patent Cooperation Treaty

[Submission date] October 2, 2001 (2001.10.2)

[Procedure Amendment 1]

[Document name to be amended] Statement

[Name of item to be amended] Claims

[Correction method] Change

[Contents of correction]

[Claims]

─────────────────────────────────────────────────── ─── Continuation of front page (51) Int.Cl. ⁷ Identification code FI theme code (reference) G01N 27/414 G01N 27/30 341U 27/416 27/46 338 33/487 336G 386G 386Z 353A 353Z 27/30 301F 301R 27/46 371G 321 381

Claims (28)

[Claims] 1. A general-purpose transducer for chemical sensor analysis or biosensor analysis used for measuring a substance concentration or ionic activity in a fluid, comprising: a first (1) and a second (2) flat carrier layer. A carrier having: at least one perforation (4.1 to 4.5, 5.1 to 5.5) provided in each of the two carrier layers (1, 2); At least one continuous layer formed by perforations (4,5) in each of two carrier layers and extending from the first active surface of the carrier onto the first and second carrier layers (1, 2). A cavity; -a filling (9) which is arranged in the cavity and which can come into contact with the analyte in the region of the first active surface (10) of the carrier; -one of the two carrier layers (1,2) Of the first At least one electrically conductive layer (8) disposed at least partially on the surface opposite the active surface (10) and in contact with said filling (9). Characteristic general-purpose transducer. 2. General-purpose transducer according to claim 1, characterized in that the carrier has another flat carrier layer (3). 3. The further flat carrier layer (3) at least partly has further perforations (6.1-6.5) connecting to at least one cavity. The general-purpose transducer according to claim 2. 4. General-purpose transducer according to claim 3, characterized in that the filling (9) is arranged in the further perforation (6.1-6.5). 5. The one packing (9) or the plurality of packings comprises a substance-detecting membrane and / or a gel.
The general-purpose transducer according to claim 4. 6. The surface of said first carrier layer (1) and / or said second carrier layer (2) and / or said further carrier layer (3), said first active surface (10) On the opposite surface, at least in part, at least one conductive layer (7
, 8) are arranged. The general-purpose transducer according to claim 1, wherein 7. At least one of said perforations (4) is provided with said first active surface (
The general-purpose transducer according to any one of claims 1 to 6, wherein the general-purpose transducer is formed so as to be conically tapered toward 10). 8. The electrically conductive layer (7, 8) extends at least partially towards the sidewalls of the adjacent perforations (4, 5). General-purpose transducer described in. 9. Another membrane, wherein said first active surface (10) comprises, for example, a gas-permeable membrane in the area of the perforations of said carrier layer (1) adjacent to said first active surface (10). The general-purpose transducer according to any one of claims 1 to 8, which is covered with (13). 10. Universal transducer according to claim 9, characterized in that the thickness of the further membrane (13) is between 1 μm and a few μm. 11. The another membrane (13) is polyvinyl chloride (PVC).
, Polyethylene (PE), polyoxymethylene (POM), polycarbonate (
PC), ethylene / propylene copolymer COP (EPDM), polyvinylidene chloride (PVDC), polyvinyl butyral (PVB), cellulose acetate (C
A), polypropylene (PP), polymethylmethacrylate (PMMA), polyamide (PA), tetrafluoroethylene / hexafluoropropylene copolymer COP (FEP), polytetrafluoroethylene (PTFE), phenol formaldehyde (PF), epoxide (EP), polyurethane (PUR), polyester (UP), silicone, melamine formaldehyde (MF), urea formaldehyde (UF), aniline formaldehyde or Kapton, characterized by the above-mentioned. General-purpose transducer. 12. The conductive layer (14) according to claim 9, characterized in that it is arranged between the first active surface (10) and the further membrane (13). A general-purpose transducer described in. 13. The cavity according to claim 1, characterized in that its surface opposite the first active surface (10) is covered by a capsule filling material (11). General-purpose transducer described in. 14. The general-purpose transducer according to claim 13, wherein the capsule filling material (11) is formed of an epoxide resin. 15. The perforations are at least partly different fillings (9, 9 ..
3. The general-purpose transducer according to claim 1, wherein the general-purpose transducer includes: 16. A channel carrier (18) with a channel (20) and a channel cover (19) arranged thereon are arranged on the first active surface (10) to form the channel (20). In the area of the first active surface (10),
General-purpose transducer according to any one of claims 1 to 15, characterized in that it is adapted to contact at least one of said perforations (4.1-4.3) in said carrier layer (1). 17. General-purpose transducer according to claim 16, characterized in that the channel carrier (18) and / or the channel cover (19) has a thickness of a few μm to a few mm, in particular a few hundred μm. 18. At least one of the carrier layers (1, 2, 3) is
Polyvinyl chloride (PVC), polyethylene (PE), polyoxymethylene (PO)
M), polycarbonate (PC), ethylene / propylene copolymer COP (EP
DM), polyvinylidene chloride (PVDC), polyvinyl butyral (PVB),
Cellulose acetate (CA), polypropylene (PP), polymethyl methacrylate (PMMA), polyamide (PA), tetrafluoroethylene / hexafluoropropylene copolymer COP (FEP), polytetrafluoroethylene (P
TFE), phenol formaldehyde (PF), epoxide (EP), polyurethane (PUR), polyester (UP), silicone, melamine formaldehyde (MF), urea formaldehyde (UF), aniline formaldehyde, Kapton, etc., or silicon, ceramic or glass. The general-purpose transducer according to any one of claims 1 to 18, comprising a synthetic material such as. 19. The method according to claim 1, wherein at least one of the carrier layers (1, 2, 3) has a thickness of a few μm to a few mm, in particular a few hundred μm. A general-purpose transducer described in. 20. At least one of said conductive layers (7, 8) is formed from a metal, in particular a noble metal such as platinum, gold, silver, or an alloy, or a screen printing paste, for example based on graphite or a metallic material. The general-purpose transducer according to any one of claims 1 to 19, wherein the general-purpose transducer is provided. 21. The thickness of at least one of said conductive layers (7, 8) is 1
21. The general-purpose transducer according to claim 1, wherein the general-purpose transducer has a size of μm to several μm. 22. The packing (9) is made of polyvinyl chloride PV as a membrane.
C, silicone, polyurethane or the like is included, or gelatin, polyvinyl alcohol (PVA) or the like is included as the gel (9).
The general-purpose transducer according to claim 21. 23. The general-purpose transducer according to claim 1, wherein the filling material contains a biological component such as an enzyme, a microorganism, or an antibody. 24. The diameter of at least one of the perforations (4.1 to 4.5) of the carrier layer (1) adjacent to the first active surface (10) is such that The general-purpose transducer according to any one of claims 1 to 23, characterized in that the thickness is several µm to several mm, especially several tens to several hundred µm. 25. The carrier comprises two cavities (4.2, 5.2, 6.2 and 4.4 and 5.4, 6.4) and a filling located inside each of the cavities. And the filler placed in one of the cavities is in contact with a first conductive layer that functions as a reference electrode, and the filler placed in the other of the cavities is a different carrier. Contacting a second or third conductive layer disposed on the layer and functioning as an actuating or counter electrode for receiving an electric current, said first and second and third conductive layers being a three-pole device for amperometric measurement. The general-purpose transducer according to any one of claims 1 to 24, wherein 26. The carrier comprises a third cavity in which a potentiometric electrode is formed and which is in contact with another conductive layer which is measurable relative to the reference electrode. The general-purpose transducer according to claim 25, wherein an object is arranged. 27. Use of the general-purpose transducer according to any one of claims 1 to 26 as a reference electrode, a sensor element for potentiometric titration measurement of analyte concentration or ion activity, and / or a sensor element for amperometric titration measurement. how to. 28. A general-purpose transducer according to claim 27 for measuring the concentration of dissolved carbon dioxide, oxygen, glucose and / or other metabolites and / or urea, or for measuring pH values or other parameters. How to use.