CA2146246A1 - Improvements in and relating to gas-permeable membranes for amperometric gas electrodes and uses thereof - Google Patents
Improvements in and relating to gas-permeable membranes for amperometric gas electrodes and uses thereofInfo
- Publication number
- CA2146246A1 CA2146246A1 CA002146246A CA2146246A CA2146246A1 CA 2146246 A1 CA2146246 A1 CA 2146246A1 CA 002146246 A CA002146246 A CA 002146246A CA 2146246 A CA2146246 A CA 2146246A CA 2146246 A1 CA2146246 A1 CA 2146246A1
- Authority
- CA
- Canada
- Prior art keywords
- gas
- electrode
- permeable
- oxygen
- amperometric
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
- G01N27/403—Cells and electrode assemblies
- G01N27/404—Cells with anode, cathode and cell electrolyte on the same side of a permeable membrane which separates them from the sample fluid, e.g. Clark-type oxygen sensors
-
- C—CHEMISTRY; METALLURGY
- C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
- C12Q—MEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
- C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
- C12Q1/001—Enzyme electrodes
- C12Q1/002—Electrode membranes
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
- G01N27/28—Electrolytic cell components
- G01N27/30—Electrodes, e.g. test electrodes; Half-cells
- G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
- G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
Abstract
A method of manufacturing a gas-permeable membrane (11) for an amperometric gas electrode comprises demetallising areas (16) of a metallised film (12) to obtain a regular array of gas-permeable micropores. Devices incorporating gas-permeable membranes used as electrodes are disclosed inter alia for analyte determinations and oxygen (e.g. BOD) measurements.
Description
~ W 0 94/08236 21 ~ 62~ 6 PCT/GB93/02076 GAS PERMEABLE MEMBRANES FOR AMPEROMETRIC GAS ELECTRODES AND USES THEREOF
R~RGROUnDD 0~ TH~ lNV~N-l10~
1. Field of the Invention The electrochemical amperometric detection of redox gases such as oxygen is a well established technique, and the electrode used in such a technique is often referred to as a "Clark Electrode". In the case of an oxygen Clark Electrode, this detection is based on oxygen transport 10 through a gas-permeable membrane to an enclosed electrolyte solution, and the subse~uent reduction of oxygen dissolved in this solution, usually on a platinum or gold sensing electrode. The potential-of this sensing electrode is held at negative potential compared to the potential of the 15 electrolyte solution by use of a reference electrode, classically a silver/silver chloride electrode. A schematic diagram illustrating this conventional approach is shown in Figure 1 of the accompanying drawings.
The response time of classical detection devices, where 20 the sensing electrode, on which the electrochemical reaction takes place, is separated from the gas-permeable membrane by a thin (e.g. a submillimeter thick) layer of electrolyte solution, is more than 100 seconds. The response time is limited by the linear diffusion rate of the redox gas 25 through the gas-permeable membrane and into the electrolyte solution as depicted in Figure 1.
The present invention is based on the use of gas-permeable polymer films (for example films a few microns thick of e.g. polypropylene or polyester) metallised on one 30 side (e.g. with gold or platinum). Such metallised films are commercially available and are currently used in the food packaging industry.
At the heart of the present invention is the use of a novel type of composite gas-permeable membrane which has W094/08236 PCT/GB93/02076 ~
21462~
been manufactured by demetallising (e.g. by using W excimer laser photoablation) areas of a metallised polymer film, to obtain a regular array of gas-permeable micropores each having a diameter or width of a few microns. The micropores 5 can be in the form of microdiscs and/or microbands, since the shape of each area is of secondary importance.
?
R~RGROUnDD 0~ TH~ lNV~N-l10~
1. Field of the Invention The electrochemical amperometric detection of redox gases such as oxygen is a well established technique, and the electrode used in such a technique is often referred to as a "Clark Electrode". In the case of an oxygen Clark Electrode, this detection is based on oxygen transport 10 through a gas-permeable membrane to an enclosed electrolyte solution, and the subse~uent reduction of oxygen dissolved in this solution, usually on a platinum or gold sensing electrode. The potential-of this sensing electrode is held at negative potential compared to the potential of the 15 electrolyte solution by use of a reference electrode, classically a silver/silver chloride electrode. A schematic diagram illustrating this conventional approach is shown in Figure 1 of the accompanying drawings.
The response time of classical detection devices, where 20 the sensing electrode, on which the electrochemical reaction takes place, is separated from the gas-permeable membrane by a thin (e.g. a submillimeter thick) layer of electrolyte solution, is more than 100 seconds. The response time is limited by the linear diffusion rate of the redox gas 25 through the gas-permeable membrane and into the electrolyte solution as depicted in Figure 1.
The present invention is based on the use of gas-permeable polymer films (for example films a few microns thick of e.g. polypropylene or polyester) metallised on one 30 side (e.g. with gold or platinum). Such metallised films are commercially available and are currently used in the food packaging industry.
At the heart of the present invention is the use of a novel type of composite gas-permeable membrane which has W094/08236 PCT/GB93/02076 ~
21462~
been manufactured by demetallising (e.g. by using W excimer laser photoablation) areas of a metallised polymer film, to obtain a regular array of gas-permeable micropores each having a diameter or width of a few microns. The micropores 5 can be in the form of microdiscs and/or microbands, since the shape of each area is of secondary importance.
?
2. Description of the Related Art ~
Our prior International application published as WO
9108474 discloses the use of photoablation for the creation 10 of apertures in electrically insulating material when creating microelectrodes and EP-A-0494382 discloses the creation of an electrochemical cell in which photoablation is used to drill holes in an insulating substrate of the cell and to expose metallised areas on the substrate. EP-A-15 0494382 does disclose a gas-permeable membrane but not one subjected to subsequent thinning (e.g. by photoablation)~
Sr~ Y 0~ TB lNVlSN-l'lON
According to one aspect of the invention there is provided a method of manufacturing a gas-permeable membrane 20 for an amperometric gas electrode from a polymer film metallised on one surface thereof which method comprises demetallising areas of the metallised film to obtain a regular array of gas-permeable micropores having a diameter or width of a few microns.
The polymer film can be inherently gas-permeable when demetallised, but if made of non-permeable material can be made gas-permeable over the localised areas where demetallisation is effected.
Conveniently, the regular array of micropores is 30 obtained by excimer laser photoablation, preferably using a W excimer laser. The metallised film is desirably of gold or platinum and the polymer film preferably is polypropylene or polyester.
W094/08236 21 ~ 6 21 6 PCT/GB93/02076 Suitably each micropore comprises a porous plug replacing film material removed in the demetallising process.
An amperometric gas electrode made by the method of the 5 invention represents a further aspect of this invention as do disposable devices using such electrodes and incorporating enzymes or microbes for controlled biological testing methods.
BRIEP DFSCRIPTION OF T~ DRAWI~GS
The invention will now be further described, by way of example, with reference to the accompanying drawings, in which:
Figure 1 is a schematic view of a classical amperometric oxygen electrode, Figure 2 is a schematic view of a first embodiment of electrode in accordance with this invention, Figure 3 is a view of the diffusion field applicable to an electrode as shown in Figure 2, Figures 4 and 5 are views corresponding to Figures 2 20 and 3 applicable to a second embodiment of electrode in accordance with the invention, Figure 6 is a schematic sectional side view of a composite gas-liquid-liquid electrode in accordauce with the invention, Figure 7 is a schematic cross-sectional view of a cell for determining BOD or sample toxicity according to the invention, Figure 8 shows one method of making an electrode membrane for use in the electrodes of Figures 2 and 4, Figure 9 schematically illustrates one form of electrode mounted on a support, and Figure 10 is an enlarged sectional view of a modified 5 arrangement of electrode and support therefor.
DESCRIPTION O~ PREFERRED ~MBODIMENTS
As already discussed ~igure 1 illustrates a prior art arrangement in which the oxygen gas permeates through a permeable membrane 11 into an electrolyte solution 14 where 10 chemical reaction occurs in the presence of a sensing electrode 12 and reference electrodes 15.
An oxygen electrode device according to the present invention which includes a novel gas-permeable membrane is illustrated in Figure 2 and comprises a gas-permeable 15 polymer film 11 having a metallic electrode layer 12 provided with demetallised microareas 16, a thin layer of an electrolyte solution 14 and a reference electrode 15 which can be a silver/silver chloride electrode.
Because oxygen cannot permeate through the metallic 20 layer 12, oxygen flow between the analyte and the internal electrolyte solution 14, can only occur through the demetallised microareas 16. The oxygen flowing through these areas can then be classically electrochemically reduced. The collection efficiency of the metallic 25 electrode layer 12, e.g. of gold or platinum, for the reduction of the oncoming oxygen is very high due to the micronic dimension of the demetallised areas. Furthermore, the electrode layer 12 cannot be closer to the membrane 11 than in the arrangement illustrated, and therefore the need 30 for diffusion of oxygen through the electrolyte solution 14 is obviated. Both of these innovative features combine to provide improvements in the oxygen electrode performance.
~ W094/08236 21~ 6 2 4 6 PCT/GB93/02076 The flux of oxygen through the gas-permeable membrane 11 however is not homogeneous as in a classical oxygen electrode (employing flux by linear diffusion as shown by dashed line arrows in Figure 1) but converges to each 5 demetallised microarea 16 as shown by the dashed-line arrows in Figure 3. In the case of the microareas 16 being microdiscs, this results in a pseudo hemispherical diffusion regime, where each demetallised microdisc 16 acts as a sink for the oxygen present in a hemispherical diffusion shell 17 10 above it, an arrangement expected to lead to a steady state flux of oxygen with reduced dependence on the flow of the analyte above the membrane 11. The oxygen flux density through the microdisc 16 is much higher than that provlded by simple linear diffusion processes; thus providing higher 15 local oxygen concentration near the reducing electrode 12.
A further advantage of a manufacturing method according to this invention is that the thickness of the gas-permeable membrane 11 can be reduced by the demetallising process (e~g~ if more laser pulses than those necessary for a 20 demetallisation photoablation process are used). This allows further tailoring of the permeation properties of the membrane 11 and therefore leads to a reduction of the response time of the electrode device.
A modification of the invention is to use the same 25 demetallising agent (e.g. a W excimer laser photoablation system)~ not only to demetallise over the required areal pattern but also to drill at least partly through the thin polymer layer. When drilling fully through the polymer film (as shown in Figure 4) it is not necessary to use a gas-30 permeable polymer film since the microhole arrangement socreated can then be filled by a plug 18 of a phase which is highly oxygen permeable, e.g. a plug of silicon material.
This hole filling or plugging procedure can be carried out, for example, by a screen printing method or a casting 35 method. In this modified approach, the array of filled microholes represent an array of oxygen micropores and W094/08236 2 1 ~ 6 ~ ~ 6 - 6 - PCT/GB93/02076 because the dimensions of the filled microholes are on the micron scale, the diffusion of oxygen to these microdiscs is controlled by a regime of part-spherical diffusion similar to that observed for the diffusion of reactants to a 5 microdisc electrode array of similar dimensions created in a still coherent gas-permeable film as sh`own in Figure 2.
The difference in the gas diffusion fields between the classical case, i.e. linear diffusion, and the part-spherical gas diffusion field which arises with the use of 10 an electrode according to this invention is thought to be the main source of the advantages achieved by the present patent application. Indeed, linear gas diffusion fields cannot yield steady state regimes and any technique based on this type of mass transfer requires a calibration procedure.
15 In contrast, the use of a part-spherical diffusion field is by nature much more efficient as it gathers redox gas from a wider volume, and consequently yields a steady state gas diffusion field. In the case of the amperometric determination of oxygen, this means the generation of a 20 constant reduction current which is a function of the geometry of the device, the diffusion coefficient of oxygen (which is a function of temperature) and the concentration it is wished to measure. If the geometry of the electrode device and the temperature are known, then the concentration 25 can be directly and accurately calculated without resorting to time-consuming calibration procèdures.
This generic proposed method for the amperometric detection of oxygen is particularly well suited for the design of biosensors where an enzyme (E), say glucose 30 oxidase, competes with the device for the oxygen dissolved in the analyte. Many biosensors based on the classical oxygen electrode have been proposed. The response of the devices hitherto proposed is limited by the physical distance between the enzymes, the membrane and the 35 electrode. By the nature of the proposed novel design, the enzymes can be immobilised on the thin polymer film. In this W094/08236 21 ~ 6 2 4 6 PCT/GB93/02076 way, the distance between the enzyme-membrane and the membrane-electrode is reduced which in turn results in a reduced response time. Although enzymes can also be immobilised on the gas-permeable membrane of a classlcal S "Clark Electrode", they tend to hinder the linear flux of oxygen. In the case of an electrode according to this invention however, the "active" surface, i.e. the surface area directly above the demetallised microdiscs represents less than 1% of the total surface area, yet the part-10 spherlcal diffusion fields can be arranged to cover themajority of the sensor surface by an appropriate choice of the density of the array of micropores. It is possible to limit the enzyme immobilisation in areas not overlaying the demetallised microareas by using the modified approach of 15 creating filled micropores. Indeed, the difference in materials used for the membrane 11 and the micropore filling material phase 18 allows the enzyme immobilisation to occur only on the film but not on the micropore filling phase.
Coupling with oxidases Numerous analytes can be determined via oxygen depletion in the presence of the appropriate enzyme. For example, cholesterol reacts with oxygen in the presence of cholesterol oxidase to form cholestenone. The rate of this reaction depends on the concentrations of enzyme and 25 substrate and on the partial pressure of oxygen in the sample. Thus a simple device for determining cholesterol would comprise an electrode or array of electrodes for determining the background oxygen tension and an enzyme modified array for determining oxygen tension in the 30 presence of the enzyme reaction (i.e. in the manner shown in Figure 3). The enzyme could be immobilised onto local areas of the surface of the gas membrane or alternatively the sensor could comprise two compartments, one containing the enzyme and one without. The cholesterol concentration would 35 conveniently be calculated by comparing the oxygen responses on the two parts of the sensor. The same principle could be used to determine many other analytes. for example glucose W094/08236 2 ~ ~ 6 2 4 ~ PCT/GB93/02076 (using glucose oxidase), phenols (using polyphenol oxidase), xanthine (using xanthine oxidase) and so on.
Similarly, other analytes can be determined by the amperometric detection of enzymically produced ammonia.
5 Examples are urea (using urease) and creatinine using creatinine imminase. The amperometricidetermination of ammonia can be effected either by inclusion of a redox marker species such as bromocresol green in an electrolyte solution 14 shown in Figure 6 or by transfer of the ammonium 10 ion across a supported liquid-liquid interface. In Figure 6, ammonia diffuses across a gas-permeable membrane 11 and dissolves as ammonium ions in the electrolyte solutions in the aqueous phase 14. Each ammonium ion is then driven across the interface into a supported non-aqueous phase 40 15 by the application of an appropriate potential difference between the electrodes 12 and lS. The ammonia concentration can then be calculated from the ion transfer current.
Biological O~yy~ Demand In specific embodiments of a device according to the 20 invention an oxygen electrode can be used in conjunction with microbes to determine biological oxygen demand (BOD) or toxicity. Thus in Figure 7 the respiration rate of microbes (e.g. freeze-dried microbes) held in a layer 41 in close proximity with a gas-permeable membrane 11 is determined by 25 the BOD of the sample. A high BOD will result in a rapidly changing oxygen tension whereas a low BOD will result in a fairly constant oxygen measurement. One of the main advantages the micro-electrode configuration brings to this measurement is that the micro-electrode itself consumes very 30 little oxygen and so does not perturb the measurement. A
total toxicity test kit would include a layer 41 loaded with microbes and nutrient next to the gas-permeable membrane.
Since both of these devices measure oxygen depletion in the sample, a sample cham~er 42 is included to minimi se oxygen 35 ingress from the atmosphere.
W094/08236 21 4 6 2 ~ 6 PCT/GB93/02076 An oxygen electrode or biosensor in accordance with this invention can be manufactured by a continuous reel to reel process, as shown in Figure 8 where a web 30 of metallised film passes from a supply spool 31 to a wind-up 5 spool 32. In its passage between spools a pattern of apertures set by a mask 33 is formed in the web 30 by photoablation at a station 34 using ultra violet laser light 35 from a source not shown. The ablation can be effected "on the fly" or in a dwell period following each advance of 10 the web by a pre-set amount. Downstream of the photoablation station 34 is a hole-filling station 36 where the holes formed in the web at station 34 are filled with an appropriate plug of gas-permeable material. A squeegee 37 schematically illustrates this stage.
In addition to the two types of system discussed in Figures 6 and 7 further systems are possible using a filled web as created by the process shown in Figure 8.
Firstly, a stick electrode approach can be employed where the film is secured to (e.g. clipped on) a body 20 cont~i ni ~g the reference electrode, and the electrolyte solution; very much like a prior art commercially available oxygen electrode. The main difference being that the platinum or gold electrode on which the electrochemical reduction takes place is attached to the gas-permeable 25 membrane, and that therefore electrical contact should be made to the latter (see Figure 9). In Figure 9 the reference electrode is shown at 19, the containing body at 20, and a metal contact to the metallised film of membrane 21 is shown at 22. Neither the film nor the clip is shown 30 in Figure 9.
Figure 10 shows an arrangement in which a web 11 of polymer film having a working electrode 12 on its lower face and containing plugged micropores 16 is supported above a support 19 carrying a reference electrode 15. Spacers 20 of 35 dielectric material hold electrodes 12 and 15 apart to W094/08236 214 ~ 2 4 ~ PCT/GB93/02076 contain a layer of electrolyte 14 therebetween. Both of the electrodes 12 and 15 and the spacers 20 can be created by screen printing and the electrolyte solution can also be printed as part of the process (i.e. it can be in the form 5 of an aqueous gel or hydrogel).
.
r
Our prior International application published as WO
9108474 discloses the use of photoablation for the creation 10 of apertures in electrically insulating material when creating microelectrodes and EP-A-0494382 discloses the creation of an electrochemical cell in which photoablation is used to drill holes in an insulating substrate of the cell and to expose metallised areas on the substrate. EP-A-15 0494382 does disclose a gas-permeable membrane but not one subjected to subsequent thinning (e.g. by photoablation)~
Sr~ Y 0~ TB lNVlSN-l'lON
According to one aspect of the invention there is provided a method of manufacturing a gas-permeable membrane 20 for an amperometric gas electrode from a polymer film metallised on one surface thereof which method comprises demetallising areas of the metallised film to obtain a regular array of gas-permeable micropores having a diameter or width of a few microns.
The polymer film can be inherently gas-permeable when demetallised, but if made of non-permeable material can be made gas-permeable over the localised areas where demetallisation is effected.
Conveniently, the regular array of micropores is 30 obtained by excimer laser photoablation, preferably using a W excimer laser. The metallised film is desirably of gold or platinum and the polymer film preferably is polypropylene or polyester.
W094/08236 21 ~ 6 21 6 PCT/GB93/02076 Suitably each micropore comprises a porous plug replacing film material removed in the demetallising process.
An amperometric gas electrode made by the method of the 5 invention represents a further aspect of this invention as do disposable devices using such electrodes and incorporating enzymes or microbes for controlled biological testing methods.
BRIEP DFSCRIPTION OF T~ DRAWI~GS
The invention will now be further described, by way of example, with reference to the accompanying drawings, in which:
Figure 1 is a schematic view of a classical amperometric oxygen electrode, Figure 2 is a schematic view of a first embodiment of electrode in accordance with this invention, Figure 3 is a view of the diffusion field applicable to an electrode as shown in Figure 2, Figures 4 and 5 are views corresponding to Figures 2 20 and 3 applicable to a second embodiment of electrode in accordance with the invention, Figure 6 is a schematic sectional side view of a composite gas-liquid-liquid electrode in accordauce with the invention, Figure 7 is a schematic cross-sectional view of a cell for determining BOD or sample toxicity according to the invention, Figure 8 shows one method of making an electrode membrane for use in the electrodes of Figures 2 and 4, Figure 9 schematically illustrates one form of electrode mounted on a support, and Figure 10 is an enlarged sectional view of a modified 5 arrangement of electrode and support therefor.
DESCRIPTION O~ PREFERRED ~MBODIMENTS
As already discussed ~igure 1 illustrates a prior art arrangement in which the oxygen gas permeates through a permeable membrane 11 into an electrolyte solution 14 where 10 chemical reaction occurs in the presence of a sensing electrode 12 and reference electrodes 15.
An oxygen electrode device according to the present invention which includes a novel gas-permeable membrane is illustrated in Figure 2 and comprises a gas-permeable 15 polymer film 11 having a metallic electrode layer 12 provided with demetallised microareas 16, a thin layer of an electrolyte solution 14 and a reference electrode 15 which can be a silver/silver chloride electrode.
Because oxygen cannot permeate through the metallic 20 layer 12, oxygen flow between the analyte and the internal electrolyte solution 14, can only occur through the demetallised microareas 16. The oxygen flowing through these areas can then be classically electrochemically reduced. The collection efficiency of the metallic 25 electrode layer 12, e.g. of gold or platinum, for the reduction of the oncoming oxygen is very high due to the micronic dimension of the demetallised areas. Furthermore, the electrode layer 12 cannot be closer to the membrane 11 than in the arrangement illustrated, and therefore the need 30 for diffusion of oxygen through the electrolyte solution 14 is obviated. Both of these innovative features combine to provide improvements in the oxygen electrode performance.
~ W094/08236 21~ 6 2 4 6 PCT/GB93/02076 The flux of oxygen through the gas-permeable membrane 11 however is not homogeneous as in a classical oxygen electrode (employing flux by linear diffusion as shown by dashed line arrows in Figure 1) but converges to each 5 demetallised microarea 16 as shown by the dashed-line arrows in Figure 3. In the case of the microareas 16 being microdiscs, this results in a pseudo hemispherical diffusion regime, where each demetallised microdisc 16 acts as a sink for the oxygen present in a hemispherical diffusion shell 17 10 above it, an arrangement expected to lead to a steady state flux of oxygen with reduced dependence on the flow of the analyte above the membrane 11. The oxygen flux density through the microdisc 16 is much higher than that provlded by simple linear diffusion processes; thus providing higher 15 local oxygen concentration near the reducing electrode 12.
A further advantage of a manufacturing method according to this invention is that the thickness of the gas-permeable membrane 11 can be reduced by the demetallising process (e~g~ if more laser pulses than those necessary for a 20 demetallisation photoablation process are used). This allows further tailoring of the permeation properties of the membrane 11 and therefore leads to a reduction of the response time of the electrode device.
A modification of the invention is to use the same 25 demetallising agent (e.g. a W excimer laser photoablation system)~ not only to demetallise over the required areal pattern but also to drill at least partly through the thin polymer layer. When drilling fully through the polymer film (as shown in Figure 4) it is not necessary to use a gas-30 permeable polymer film since the microhole arrangement socreated can then be filled by a plug 18 of a phase which is highly oxygen permeable, e.g. a plug of silicon material.
This hole filling or plugging procedure can be carried out, for example, by a screen printing method or a casting 35 method. In this modified approach, the array of filled microholes represent an array of oxygen micropores and W094/08236 2 1 ~ 6 ~ ~ 6 - 6 - PCT/GB93/02076 because the dimensions of the filled microholes are on the micron scale, the diffusion of oxygen to these microdiscs is controlled by a regime of part-spherical diffusion similar to that observed for the diffusion of reactants to a 5 microdisc electrode array of similar dimensions created in a still coherent gas-permeable film as sh`own in Figure 2.
The difference in the gas diffusion fields between the classical case, i.e. linear diffusion, and the part-spherical gas diffusion field which arises with the use of 10 an electrode according to this invention is thought to be the main source of the advantages achieved by the present patent application. Indeed, linear gas diffusion fields cannot yield steady state regimes and any technique based on this type of mass transfer requires a calibration procedure.
15 In contrast, the use of a part-spherical diffusion field is by nature much more efficient as it gathers redox gas from a wider volume, and consequently yields a steady state gas diffusion field. In the case of the amperometric determination of oxygen, this means the generation of a 20 constant reduction current which is a function of the geometry of the device, the diffusion coefficient of oxygen (which is a function of temperature) and the concentration it is wished to measure. If the geometry of the electrode device and the temperature are known, then the concentration 25 can be directly and accurately calculated without resorting to time-consuming calibration procèdures.
This generic proposed method for the amperometric detection of oxygen is particularly well suited for the design of biosensors where an enzyme (E), say glucose 30 oxidase, competes with the device for the oxygen dissolved in the analyte. Many biosensors based on the classical oxygen electrode have been proposed. The response of the devices hitherto proposed is limited by the physical distance between the enzymes, the membrane and the 35 electrode. By the nature of the proposed novel design, the enzymes can be immobilised on the thin polymer film. In this W094/08236 21 ~ 6 2 4 6 PCT/GB93/02076 way, the distance between the enzyme-membrane and the membrane-electrode is reduced which in turn results in a reduced response time. Although enzymes can also be immobilised on the gas-permeable membrane of a classlcal S "Clark Electrode", they tend to hinder the linear flux of oxygen. In the case of an electrode according to this invention however, the "active" surface, i.e. the surface area directly above the demetallised microdiscs represents less than 1% of the total surface area, yet the part-10 spherlcal diffusion fields can be arranged to cover themajority of the sensor surface by an appropriate choice of the density of the array of micropores. It is possible to limit the enzyme immobilisation in areas not overlaying the demetallised microareas by using the modified approach of 15 creating filled micropores. Indeed, the difference in materials used for the membrane 11 and the micropore filling material phase 18 allows the enzyme immobilisation to occur only on the film but not on the micropore filling phase.
Coupling with oxidases Numerous analytes can be determined via oxygen depletion in the presence of the appropriate enzyme. For example, cholesterol reacts with oxygen in the presence of cholesterol oxidase to form cholestenone. The rate of this reaction depends on the concentrations of enzyme and 25 substrate and on the partial pressure of oxygen in the sample. Thus a simple device for determining cholesterol would comprise an electrode or array of electrodes for determining the background oxygen tension and an enzyme modified array for determining oxygen tension in the 30 presence of the enzyme reaction (i.e. in the manner shown in Figure 3). The enzyme could be immobilised onto local areas of the surface of the gas membrane or alternatively the sensor could comprise two compartments, one containing the enzyme and one without. The cholesterol concentration would 35 conveniently be calculated by comparing the oxygen responses on the two parts of the sensor. The same principle could be used to determine many other analytes. for example glucose W094/08236 2 ~ ~ 6 2 4 ~ PCT/GB93/02076 (using glucose oxidase), phenols (using polyphenol oxidase), xanthine (using xanthine oxidase) and so on.
Similarly, other analytes can be determined by the amperometric detection of enzymically produced ammonia.
5 Examples are urea (using urease) and creatinine using creatinine imminase. The amperometricidetermination of ammonia can be effected either by inclusion of a redox marker species such as bromocresol green in an electrolyte solution 14 shown in Figure 6 or by transfer of the ammonium 10 ion across a supported liquid-liquid interface. In Figure 6, ammonia diffuses across a gas-permeable membrane 11 and dissolves as ammonium ions in the electrolyte solutions in the aqueous phase 14. Each ammonium ion is then driven across the interface into a supported non-aqueous phase 40 15 by the application of an appropriate potential difference between the electrodes 12 and lS. The ammonia concentration can then be calculated from the ion transfer current.
Biological O~yy~ Demand In specific embodiments of a device according to the 20 invention an oxygen electrode can be used in conjunction with microbes to determine biological oxygen demand (BOD) or toxicity. Thus in Figure 7 the respiration rate of microbes (e.g. freeze-dried microbes) held in a layer 41 in close proximity with a gas-permeable membrane 11 is determined by 25 the BOD of the sample. A high BOD will result in a rapidly changing oxygen tension whereas a low BOD will result in a fairly constant oxygen measurement. One of the main advantages the micro-electrode configuration brings to this measurement is that the micro-electrode itself consumes very 30 little oxygen and so does not perturb the measurement. A
total toxicity test kit would include a layer 41 loaded with microbes and nutrient next to the gas-permeable membrane.
Since both of these devices measure oxygen depletion in the sample, a sample cham~er 42 is included to minimi se oxygen 35 ingress from the atmosphere.
W094/08236 21 4 6 2 ~ 6 PCT/GB93/02076 An oxygen electrode or biosensor in accordance with this invention can be manufactured by a continuous reel to reel process, as shown in Figure 8 where a web 30 of metallised film passes from a supply spool 31 to a wind-up 5 spool 32. In its passage between spools a pattern of apertures set by a mask 33 is formed in the web 30 by photoablation at a station 34 using ultra violet laser light 35 from a source not shown. The ablation can be effected "on the fly" or in a dwell period following each advance of 10 the web by a pre-set amount. Downstream of the photoablation station 34 is a hole-filling station 36 where the holes formed in the web at station 34 are filled with an appropriate plug of gas-permeable material. A squeegee 37 schematically illustrates this stage.
In addition to the two types of system discussed in Figures 6 and 7 further systems are possible using a filled web as created by the process shown in Figure 8.
Firstly, a stick electrode approach can be employed where the film is secured to (e.g. clipped on) a body 20 cont~i ni ~g the reference electrode, and the electrolyte solution; very much like a prior art commercially available oxygen electrode. The main difference being that the platinum or gold electrode on which the electrochemical reduction takes place is attached to the gas-permeable 25 membrane, and that therefore electrical contact should be made to the latter (see Figure 9). In Figure 9 the reference electrode is shown at 19, the containing body at 20, and a metal contact to the metallised film of membrane 21 is shown at 22. Neither the film nor the clip is shown 30 in Figure 9.
Figure 10 shows an arrangement in which a web 11 of polymer film having a working electrode 12 on its lower face and containing plugged micropores 16 is supported above a support 19 carrying a reference electrode 15. Spacers 20 of 35 dielectric material hold electrodes 12 and 15 apart to W094/08236 214 ~ 2 4 ~ PCT/GB93/02076 contain a layer of electrolyte 14 therebetween. Both of the electrodes 12 and 15 and the spacers 20 can be created by screen printing and the electrolyte solution can also be printed as part of the process (i.e. it can be in the form 5 of an aqueous gel or hydrogel).
.
r
Claims (13)
1. A method of manufacturing a gas-permeable membrane for an amperometric gas electrode from a polymer film metallised on one surface thereof which method comprises demetallising areas of the metallised film to obtain a regular array of gas-permeable micropores having a diameter or width of a few microns.
2. A method according to claim 1, in which the polymer film is inherently gas-permeable when demetallised.
3. A method according to claim 1, in which the polymer film is of non gas-permeable material but is rendered gas-permeable over the localised areas of said regular array of micropores.
4. A method according to any one preceding claim, in which the regular array of micropores is obtained by excimer laser photoablation.
5. A method according to claim 4, in which the photoablation involves the use of a UV excimer laser.
6. A method according to any one preceding claim, in which the metallised layer on the polymer film is of gold or platinum.
7. A method according to any one preceding claim, in which the polymer film is polypropylene or polyester.
8. An amperometric gas electrode comprising a membrane made by the method of any one preceding claim.
9. A redox gas detection device incorporating a gas electrode as claimed in claim 8.
10. An amperometric gas electrode comprising a membrane made by the method of claim 1 incorporating at least one enzyme for the determination of a biological species.
11. A composite electrode comprising a gas-permeable membrane fabricated in accordance with the method of claim 1 and means for providing a supported liquid-liquid interface adjacent thereto.
12. A disposable oxygen sensor incorporating a gas-permeable electrode according to claim 8 and incorporating a defined cavity which may contain microbes.
13. An amperometric gas electrode according to claim 8 in which the metallised layer serves as both gas barrier and electrode.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| GB9221099.6 | 1992-10-07 | ||
| GB929221099A GB9221099D0 (en) | 1992-10-07 | 1992-10-07 | Improvements in and relating to gas permeable membranes for amperometric gas electrodes |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2146246A1 true CA2146246A1 (en) | 1994-04-14 |
Family
ID=10723108
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002146246A Abandoned CA2146246A1 (en) | 1992-10-07 | 1993-10-06 | Improvements in and relating to gas-permeable membranes for amperometric gas electrodes and uses thereof |
Country Status (7)
| Country | Link |
|---|---|
| US (1) | US5575930A (en) |
| EP (1) | EP0663999B1 (en) |
| AT (1) | ATE176047T1 (en) |
| CA (1) | CA2146246A1 (en) |
| DE (1) | DE69323205T2 (en) |
| GB (1) | GB9221099D0 (en) |
| WO (1) | WO1994008236A1 (en) |
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-
1992
- 1992-10-07 GB GB929221099A patent/GB9221099D0/en active Pending
-
1993
- 1993-10-06 DE DE69323205T patent/DE69323205T2/en not_active Expired - Fee Related
- 1993-10-06 EP EP93922021A patent/EP0663999B1/en not_active Expired - Lifetime
- 1993-10-06 WO PCT/GB1993/002076 patent/WO1994008236A1/en active IP Right Grant
- 1993-10-06 US US08/407,002 patent/US5575930A/en not_active Expired - Fee Related
- 1993-10-06 CA CA002146246A patent/CA2146246A1/en not_active Abandoned
- 1993-10-06 AT AT93922021T patent/ATE176047T1/en not_active IP Right Cessation
Also Published As
| Publication number | Publication date |
|---|---|
| EP0663999A1 (en) | 1995-07-26 |
| DE69323205D1 (en) | 1999-03-04 |
| EP0663999B1 (en) | 1999-01-20 |
| US5575930A (en) | 1996-11-19 |
| GB9221099D0 (en) | 1992-11-18 |
| ATE176047T1 (en) | 1999-02-15 |
| WO1994008236A1 (en) | 1994-04-14 |
| DE69323205T2 (en) | 1999-07-08 |
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