IMMOBILISED ENZYME ELECTRODES AND A METHOD FOR REDUCING THE ALCOHOL SENSITIVITY

Abstract: Enzyme electrodes are described which are of reduced sensitivity to alcohol. The electrodes comprise a porous resin-­ bonded layer of powdered carbon or graphite, onto which the enzyme is immobilised, said layer containing either finely divided platinum oxide, or finely divided platinum the surface of which is provided with a thin oxide film, e.g. by an ano­ disation process, said finely divided platinum oxide or anodised platinum being uniformly dispersed throughout the resin-­ bonded carbon or graphite layer and preferably preadsorbed onto the surface of the powdered carbon or graphite prior to bonding. Also disclosed is a method of making such electrodes by a polarisation treatment of a preassembled platinised electrode.

Description: This invention relates to an improvement or modification in enzyme electrodes of the type disclosed in our previous European Patent Application No. 87304688 (Publication No. EP-A-0247850). In that application enzyme electrodes of improved sensitivity and rapid response time are disclosed and which comprise an enzyme layer immobilised onto an electrically conductive carbon substrate, more particularly an electrically conductive carbon substrate, more particularly an electrically conductive carbon substrate having a heterogeneous porous surface layer onto which the enzyme is immobilised and which consists essentially of finely divided particles of a platinum group metal, e.g. platinum or palladium, uniformly dispersed throughout a porous matrix of resin bonded carbon or graphite particles. Preferred resin binders are hydrophobic resin binders, particularly fluorocarbon resins, especially polytetrafluoroethylene. The heterogenous, porous surface layer is preferably formed as a resin bonded surface layer on an underlying electrically conductive support, e.g. a metal sheet, or more preferably, a sheet of electrically conductive carbon paper. Alternatively, the porous surface layer may be formed as a resin bonded surface layer on a filamentous web of electrically conductive fibres, e.g. a filamentous web of carbon fibres. Alternatively, the heterogenous, porous surface layer may be an integral, self-supporting layer of resin bonded carbon or graphite particles, having said finely divided platinum group metal substantially uniformly dispersed therethrough. Whilst the resin bonded carbon or graphite particle layer containing the finely divided platinum group metal can be formed by suitably moulding a uniform mixture containing said carbon or graphite particles and said finely divided platinum group metal, the finely divided platinum group metal is preferably preadsorbed onto the surface of the carbon or graphite particles, prior to the moulding thereof to form said resin bonded layer. Materials made according to that technique, which is disclosed in detail in GB-A-1,357,494, US-A-4,0444,193 and US-A-4,166,143, or in US-A-4,229,490 and US-A-4,293,396 for supported versions thereof, are in fact commercially available materials heretofore used as gas diffusion electrodes in fuel cells, and available from The Prototech Company of Newton Highlands, Massachusetts, United States of America. Whilst the novel enzyme electrodes described above and disclosed in more detail in the previous application are highly advantageous in giving extremely rapid response times, high output current densities, remarkable storage stability when wet, and require relatively low operating potentials, giving rise to low background noise, it has been found that such enzyme electrodes are alcohol sensitive, that is to say, they give rise to false readings, and a general increase of background current, in the presence of alcohol, especially ethanol, and thus cannot be used for the reliable determination of analytes, e.g. glucose, in samples containing quantities of alcohol (ethanol). In JP-A-56 163447 an enzyme electrode is disclosed comprising an electrically conductive carbon base supporting a layer of immobilised enzyme, e.g. an immobilised glucose oxidase. The electrically conductive base itself is of moulded graphite containing up to 10 parts by weight of a fluorocarbon resin as a binder, and onto which is deposited, e.g. electrolytically or by vapour deposition, a thin (less than 1µm) film of platinum. The invention allegedly avoids the problems associated with the immobilisation of the enzyme directly onto the platinum surface and produces an enzyme electrode allegedly characterised by rapid response times (5 seconds), high sensitivity and durability. However, experimental work with such electrodes and carried out in connection with the patentability of enzyme electrodes of the type disclosed in EP-A-0247850 has failed to elicit such benefits. Nor does JP-A-56 163447 have any relevance to the problem faced by the present inventors, namely countering the alcohol sensitivity of enzyme electrodes disclosed in EP-A-0247850. In US-A-4,970,145 Nakamura et al have disclosed enzyme electrodes comprising an oxidase such as glucose oxidase immobilised onto an electrically conductive graphite base containing a metal oxide, e.g. ruthenium oxide, which is capable of entering into a reversible redox reaction coupled to the reaction of the enzyme and effectively acting as an electron transfer agent between the enzyme and the electron collector, i.e. the graphite, and during the course of the enzymatic reaction. The specific objective of Nakamura et al, is to eliminate the delayed response of enzyme electrodes of that kind, i.e. involving the oxidation of H₂O₂, produced by the reaction of the enzyme, at the surface of an electron collector, that response rate being slow due to the slow rate of diffusion of the H₂O₂ to the surface of the electron collector, and sensitivity of the response of the electrode to dissolved oxygen concentrations. According to Nakamura et al, enzyme electrodes of improved response time and improved sensitivity to dissolved oxygen concentrations are obtained by first mixing RuO₂ powder with graphite powder and moulding the mixed powder into a solid disc by means of a disc press, the graphite and the RuO₂ forming one solid unit. A glucose oxidase solution is applied to the surface of the disc and the enzyme immobilised by cross-linking to the surface of the disc. In the alternative the metal oxide, i.e. the RuO₂, can be used to form a thin film on the surface of the electron collector, e.g. by thermal decomposition, electrodeposition or by vapour deposition. In yet another alternative the RuO₂ may itself serve as the electron collector and for that purpose will be deposited as a surface film on an underlying glass plate. The construction of the Nakamura et al electrode is allegedly shown in Figures 3 and 4 of US-A-4 392 933 and according to the description at column 2 line 63 to column 4, consists of a moulded disc 3 formed as one solid unit from the mixture of graphite powder (3) and RuO₂ powder (1 and 4, sic) with the enzyme (4) immobilised by cross-linking to the surface of the disc (3), the whole forming a solid state enzyme electrode (5). Insofar as that description can be understood, the Nakamura electrode appears to be a solid structure comprised of RuO₂ and graphite and having an enzyme immobilised onto the surface of that solid structure, or else a thin film of RuO₂ on the surface of a glass plate, which film acts as its own electron collector. Those electrodes therefore seem to be a very different structure from those disclosed by Bennetto et al in EP-A-0247850 and with which the present invention is concerned namely enzyme electrodes comprising an essentially porous layer of resin-bonded carbon or graphite particles containing particles of a finely-divided platinum, group metal uniformly disposed through that layer, and preferably preabsorbed onto the surface of the carbon or graphite particles prior to bonding, that porous resin-bonded layer of carbon or graphite and particles of finely divided platinum group metal having an enzyme immobilised or adsorbed onto its surface. Moreover, Nakamura clearly does not recognise the problem of alcohol sensitivity of enzyme electrodes of this general type, nor does he provide any answer to that problem, notwithstanding that, amongst many other oxides listed as suitable alternatives to RuO₂ as the electron transfer agent via a coupled redox reaction to the electron collector, platinum oxide is listed. Clearly that is considered to be a mere alternative to RuO₂, without any recognition of any special attribute, and certainly not any suggestion whatsoever of its role, now identified, in solving the problem of alcohol sensitivity in enzyme electrodes of the type described by Bennetto et al in EP 0 247 850. In Anal. Chem. (1984) 56 , 2891 - 96, Castner et al compared the Nernstian behaviour of platinum based enzyme electrodes, i.e. comprising glucose oxidase immobilised directly onto the surface of a platinum electrode, using four different methods of electrochemical surface treatment of the electrode, namely oxidation, reduction, double layer and platinic chloride, and also using a flame treated platinum surface. These were essentially potentiometric, rather than amperometric studies, and showed that gross differences did occur in the potentiometric response of such electrodes, i.e. the response of the electrode to the oxidation of H₂O₂ at the platinum surface, especially in comparison with the electrochemical oxidation of H₂O₂ using a bare platinum surface. In their conclusions, those authors reported that, whilst there was considerable variation in the potentiometric response of such sensors, the state of knowledge of platinum oxide surface chemistry and the involvement of various platinum oxide species the potentiometric response of such electrodes was too uncertain for these principles to be used in the development of a practical glucose sensor. Quite clearly the experiments of Castner et al have no relevance at all to the problem of the sensitivity of the amperometric response of platinum based electrodes of the Bennetto type to the presence of alcohol (ethanol) in the sample. In accordance with a first aspect of the present invention, it has been found that such alcohol sensitivity can be controlled by using as the finely divided platinum group metal finely divided platinum which has been subjected to a controlled oxidation treatment, thereby to form a thin oxide file on the surface of the metal particles. Whilst this can be done prior to formation of the electrode substrate, i.e. before moulding the platinised carbon or graphite particles, or the powdered mixture of finely divided platinum metal and carbon or graphite, the surface oxidation can be more easily achieved by anodising the metal particles in situ , for example by subjecting the electrode material to a polarisation treatment, which may be carried out before or after immobilisation of the enzyme, preferably before. In a second aspect, it has been found that, in enzyme electrodes of the foregoing type, the platinum group metal can be substituted, in whole or in part, by platinum oxide. As previously, the electrically conductive support for the immobilised enzyme may be formed by moulding a preformed mixture of powdered carbon or graphite, powdered platinum oxide, with or without additional finely divided platinum group metal, and a resin binder, preferably a hydrophobic resin binder, e.g. a fluorocarbon resin such as polytetrafluoroethylene, into either a self-supporting porous layer of resin-bonded carbon or graphite particles having said platinum oxide, and said platinum metal if present, substantially uniformly dispersed throughout said layer, or more preferably, as a porous surface layer on an underlying, preferably electrically conductive support, e.g. of metal, electrically conductive carbon paper or a carbon fibre fabric. More preferably, however, the platinum oxide, with or without additional platinum metal, is adsorbed onto the surface of the carbon or graphite powder particles prior to bonding with said resin. Alternatively, in accordance with the first aspect of the present invention, there may be used finely divided platinum metal, the particle surface of which is oxidised under controlled conditions to form a thin oxide film thereon, either before or after the adsorption thereof onto the carbon or graphite particles. As the carbon powder there may be used any suitable carbon or graphite powder which readily permits the subsequent immobilisation of the enzyme, and to this end, carbon powders should be used having a high density of functional groups, such as carboxylate, amino and sulphur-containing groups, on the surface, as opposed to the more vitreous and glassy carbons, which bind enzymes only poorly. Particle size may range from 3 to 50 nm, more usually 5 to 30 nm. Platinum oxide, which term is hereinafter used to embrace oxidised, e.g. anodised, particles of platinum, may be deposited onto the carbon particles in any convenient fashion, e.g. by adsorption onto the carbon and graphite particles from suspension in a suitable liquid vehicle, to give platinum oxide loadings of from 0.1 to 20% by weight, based on the weight of carbon, preferably from 0.5 to 5%. These limits are, however, practical rather than critical. Below about 0.1% platinum oxide the output signal falls to a level which, in practical terms, is too low to be measured except by very sensitive apparatus. Above about 20%, the loading of platinum oxide becomes uneconomic, with little additional benefit in terms of response time, sensitivity etc. Indeed with extremely high metal loadings the sensitivity begins to fall. Following deposition or adsorption of the platinum oxide onto the carbon or graphite particles the powder is moulded using a suitable resin binder, preferably a fluorocarbon resin such as polytetrafluoroethylene to form either a completely self-supporting porous moulded structure consisting essentially of said resin bonded, oxide containing carbon powder particles, or more usually a porous moulded surface layer of such resin-bonded particles bonded to an electrically conductive substrate, e.g. of metal, carbon or graphite. A particularly preferred substrate material for the moulded, resin-bonded platinised carbon layer is carbon paper as taught by US-A-4,229,490, or an open pore carbon cloth as taught by US-A-4,293,396. In order to retain maximum porosity the amount of resin used as the binding agent should be the minimum required to provide mechanical integrity and stability to the electrode layer, such layer usually having a thickness no more than about 0.1 to 0.5 mm, although greater thicknesses may be employed. Subject to the requirements of structural integrity, mechanical strength, and porosity, amounts of binding resin are not critical and may range from as little as 5 or 10% by weight, based on the amount of oxide containing carbon powder, up to as much as 80%, but with the amount more usually in the range 30 to 70% by weight. A variety of resins may be used, including resins which are conducting or semi-conducting, but preferred are synthetic fluorocarbon resins, particularly polytetrafluoroethylene. In view of the small but essential requirement for oxygen in the oxidation process it is essential that the binder be permeable to oxygen. To this end the binder should have a minimum solubility towards oxygen at atmospheric pressure of at least 2 x 10⁻³ cm³ O₂ (measured at standard temperature and pressure) per cm³ of polymer. Suitable binders and their known oxygen solubilities taken from The Polymer Handbook (Ed. J. Brandrup and E.H. Immergut) 1st Ed. (1967), Interscience, include: S x 10² (cm³) Polytetrafluoroethylene (PTFE) 0.276 Fluorocarbon polymers other than PTFE Variable, 0.2 upwards Polyethylmethacrylate 8.6 Polystyrene 18.2 (calculated) Polyvinyl acetate 6.3 Polyvinyl chloride 2.92 Polycarbonate 0.51 Poly(4-methylpentene-1) 24.3 Polyisoprene 10.3 Polychloroprene 7.5 Poly 1,3-butadiene 9.7 Silicone rubber 31.1 The preferred enzyme electrode substrates used in accordance with this invention are, in fact, similar to those platinised carbon electrode materials sold by the Prototech Company of Newton Highlands, Massachussets, and used heretofore as electro-catalytic gas diffusion electrodes in fuel cells, but wherein the platinum component is replaced by platinum oxide, or in which the platinum component is anodised prior to adsorption onto the carbon powder. The preparation of such materials is similar to that described in detail in US-A-4,044,193, US-A-4,166,143, US-A-4,293,396 and US-A-4,478,696, to which reference should be made for full details, except that finely divided platinum oxide is used in place of the finely divided platinum, or else the finely divided platinum is given a surface oxidation, e.g. polarisation treatment, before or after adsorption of the platinum onto the carbon or graphite, and/or before or after moulding with said resin. In broad detail, however, colloidal platinum or platinum oxide with a particle size in the range 15 to 25 Angstroms (1.5 to 2.5 nm) is adsorbed onto the surface of powdered carbon (particle size 50 to 300 Angstroms : 5 to 30 nm), for example, by formation of a platinum sol in situ in the presence of powdered carbon which acts as a nucleating agent for the sol. The platinised carbon particles are then moulded onto an electrically conductive supporting structure, e.g. a sheet of carbon paper, using a synthetic resin binder, preferably a fluorinated hydrocarbon resin, and especially polytetrafluoroethylene, followed, in the case of finely divided platinum, with a surface oxidation, e.g. polarisation treatment to provide an oxidised surface on the platinum particles. In an alternative, the platinum or platinum oxide containing carbon particles may be impregnated into a preformed porous carbon cloth and bonded therein using the resin binder, preferably polytetrafluoroethylene, again before or after surface oxidation of the finely divided platinum. In another alternative, there may be used carbon paper electrodes of the type comprising a carbon paper support member, preferably impregnated with a water-repellent resin such as polytetrafluoroethylene, and onto which is deposited, e.g. by screen printing, a resin bonded catalyst layer comprising either a uniform mixture of platinum oxide and carbon or graphite particles, bonded with a resin binder, preferably again polytetrafluoroethylene, or a uniform mixture of finely divided platinum and carbon or graphite, the finely divided platinum having or being subsequently provided with a surface oxide film. The immobilisation of the enzyme on the surface of the resin-bonded, carbon substrate can be carried out using a variety of well established immobilisation techniques, for example, covalent bonding with a carbodiimide or a carbonyldiimidazole reagent, covalent bonding with 1,6-dinitro-3,4-difluorobenzene (DFDNB), or cross-linking with glutaraldehyde. Typical exemplary protocols for the immobilisation of the enzyme, glucose oxidase, are as follows: A. Carbodiimide Treatment : 1. Cut out pieces of electrode of suitable size from the sheet of electrode material. 2. Immerse the electrodes in ethanol for about 5 minutes to ensure thorough wetting of the PTFE coated binder and backing. 3. Remove the electrodes from the ethanol and wash them thoroughly with distilled water to remove all traces of ethanol. 4. Prepare 5 ml (or less) of a 0.15 M solution of 1-cyclohexyl-3-(2-morpholino)carbodiimide p -methyltoluene sulphonate in 0.1 M pH 4.5 acetate buffer and place the electrodes in this for 90 minutes at room temperature. Gentle agitation with a mechanical shaker may be used. Should the electrodes float on the surface of the solution then they have not been sufficiently wetted, and the treatment should be repeated from step 2. 5. Remove the electrodes and wash them thoroughly with distilled water. Place them in a freshly prepared solution of glucose oxidase (5.0 mg/ml) in pH 5.6 acetate buffer for 90 minutes at room temperature with gentle mechanical shaking. 6. Remove the electrodes from the enzyme solution and rinse them thoroughly with 0.1 M acetate buffer. The electrodes are now ready for use. 7. Store the electrodes at 4°C in 0.1 M pH 5.6 acetate buffer. B. Carbonyldiimidazole Treatment : 1. Carry out step 1 above and omit steps 2 and 3. 2. Prepare a solution of N,N '-carbonyldiimidazole in anhydrous dimethyl formamide (40 mg/ml). 3. Place the electrodes in this solution for 90 minutes at room temperature with gentle mechanical shaking if desired. 4. Remove the electrodes from the solution and dry off the excess carbonyldiimidazole solution before placing them in a freshly prepared solution of glucose oxidase for a further 90 minutes. 5. Carry out steps 6 and 7 above. C. DFDNB Treatment : 1. Carry out steps 1-3 under A above. 2. Wash the electrodes thoroughly in sodium borate buffer (0.1 M, pH 8.5). 3. Prepare a solution of 1,6-dinitro-3,4-difluorobenzene in methanol (0.1021 g/5 ml) and place the electrodes in this for 10 minutes at room temperature. 4. Remove the electrodes and wash them thoroughly with borate buffer before placing them in a solution of glucose oxidase for a further 90 minutes at room temperature. 5. Carry out steps 6 and 7 under A above. Other types of coupling agent may be used for the immobilisation process, including bifunctional agents of variable chain length, for example diimidates such as dimethylmalonimidate or dimethylsuberimidate. In the alternative, it has been found that simple adsorption of the enzyme onto the platinum oxide containing resin-bonded carbon powder support, i.e. without cross-linking, is effective with some enzymes, and in particular with glucose oxidase. Usually, but not necessarily, the surface layer of immobilised enzyme will be physically protected by the application of a suitably porous, e.g. polycarbonate, film or membrane which must, of course, be permeable by the enzyme substrate (glucose) which is to be determined. Such membranes are somewhat disadvantageous in increasing the response time of the sensor, but nevertheless even with such a membrane the present sensors are capable of response times comparable with, and in many cases, substantially better than, conventional enzyme electrodes. As already indicated, the invention relates particularly to glucose oxidase electrodes, i.e. in which the immobilised enzyme is a glucose oxidase, but it will be apparent that other oxidoreductases can be used, although not always with equivalent effect. This is not necessarily due to any inherent ineffectiveness of the enzyme, but to other factors. For example, in the determination of oxalic acid using oxalate oxidase the oxalic acid substrate itself undergoes electrochemical oxidation at the base electrode, thus largely masking any effect from the enzyme. However, other suitable oxidoreductases include lactate oxidase, galactose oxidase, cholesterol oxidase and other peroxide producing enzymes as well as combinations of immobilised enzymes, including combinations of a non-oxidase and an oxidase, the first acting on a substrate of interest to produce an oxidisable substrate for the oxidase, the latter acting on the oxidisable product to produce a measurable current which is proportional to the concentration of the substrate of interest. One such combination is the combination of beta-galactosidase and glucose oxidase (for the quantitative determination of lactose), or the combination of a beta-glucan depolymerising enzyme, beta-glucosidase and glucose oxidase (for the determination of beta-glucans). Other types of sensor application include the use of enzymic or non-enzymic reagents or processes which interact with a primary substrate of interest in a precursor reaction, the resulting product including a substance which in turn acts as a substrate for an enzyme electrode according to this invention. Many examples of such precursor steps will be found in the field of immunochemical reactions, and methods of using such reactions in the construction of sensors, including immunosensors, utilizing enzyme electrodes according to the present invention will be apparent to those skilled in the art. However, the primary application of the electrodes according to the invention will be as biosensors for the detection and/or quantitative measurement of an oxidisable substrate, especially glucose, in a sample, especially a clinical sample such as blood, serum, plasma, urine, sweat, tears and saliva. It is in such applications that the relative insensitivity of the present oxide containing electrode to ethanol is particularly advantageous. Other possible, non-clinical applications include: (a) fermentation monitoring, (b) industrial process control, (c) environmental monitoring, e.g. effluent and pollution control of liquids and gases, (d) food testing, (e) veterinary applications, particularly applications allied to the clinical applications suggested above. In so far as bio- and other sensors incorporating an enzyme electrode material according to the present invention may comprise other structural elements, electrical leads, electrically non-conductive (insulating) supports or probes, etc., such elements in the construction are conventional and need not be described in detail. Suffice it to say that, where, as will usually be the case, the electrode material is a paper thin sheet or wafer, the biosensor will usually include an insulating support member or probe upon which the electrode material is mounted and by means of which the electrode material can be introduced into the sample. In such cases the actual size of the piece of electrode material may be quite small, no more than a few square millimetres, or even smaller. Electrical contact with the electrode material may be made in many ways, for example, by mounting the electrode material in face to face contact with an electrically conductive contact or terminal, e.g. of platinum, silver or other suitable conductor. Where the electrode material is of sufficient thickness and strength to be completely self-supporting, insulating supports or carriers for the electrode material can be dispensed with, and electrical leads connected directly to the surface of the electrode material. In the alternative method of this invention, i.e. in situ oxidisation of the finely divided platinum metal, in enzyme electrodes of the type disclosed in GB-A-2,191,003, this may be achieved by exposing the electrically conductive substrate, before or after immobilisation of the enzyme to a polarisation treatment effective to anodise the surface of the platinum particles present in the electrode. Such a treatment may be effected by polarising the electrode substrate to a positive potential, with reference to a silver/silver chloride electrode, for a short period of time, e.g. from 1 to 30 minutes. The actual value of the applied potential is not critical, although below about +1000 mV, treatment times may become excessive. Similarly the maximum is governed by practical considerations, since too high a potential will result in too high a current density with possible consequential damage or destruction of the electrode material, to say nothing of inactivation of the enzyme. For all practical purposes polarisation at from +1000 mV to +2000 mV, measured with reference to silver/silver chloride, preferably +1200 mV to +1500 mV has been found to be satisfactory and to give reasonably short treatment times, i.e. from 1 to 30 minutes. In some cases a cyclical polarisation treatment may be used including alternate polarisation cycles at, for example, ±2 volts, preferably +1.5 volts to -1.5 volts with reference to a silver/silver chloride electrode, provided that the cyclical polarisation finishes at a positive potential with reference to silver/silver chloride. Polarisation at a negative potential, or termination at a negative potential with reference to silver/silver chloride may increase ethanol sensitivity. The reduction in ethanol sensitivity obtained with the above method is illustrated by the following data. For this purpose the current output was measured from 2 mm discs of platinised carbon paper (obtained from The Prototech Company) in the presence of 1% v/v ethanol using a cell of the type shown in Figure 15 of the drawings of GB-A-2,191,003. For the measurement of the response to ethanol, the electrode material was poised at various different potentials, as indicated, and measurements were made both before and after polarisation: The following data has been obtained using 2 mm diameter enzyme electrodes of the type disclosed in GB-A-2,191,003 and comprising glucose oxidase immobilised onto platinised carbon paper electrode material obtained from the Prototech Company, using the polarographic cell disclosed in that application, and in which the electrodes were polarised anodically before immobilisation of the enzyme. The same electrodes treated in the same way were also measured for ethanol sensitivity using a 0.2% v/v ethanol solution. Polarisation was effected in a 3-electrode cell at the potentials indicated, such potentials being with reference to a silver/silver chloride electrode: Polarisation Treatment Current µA 10mM Glucose 0.2% v/v ethanol Unpolarised electrode 6.25 1.55 +1200 mV for 10 minutes 7.0 0.25 +1200 mV for 30 minutes 6.7 0.22 +1500 mV for 10 minutes 6.8 0.14 Such results show the substantial (> 12 x) reduction in ethanol sensitivity obtained by the polarisation treatment. To illustrate the use of platinum oxide, a carbon paper electrode similar to those described in GB-A-2,191,003 but containing finely divided platinum oxide predispersed onto the carbon particles prior to bonding onto a carbon paper substrate, in place of platinum, was immersed overnight in a phosphate buffer pH 7 containing 5 mg/mL glucose oxidase. As a result glucose oxidase was adsorbed onto the surface of the platinum oxide containing carbon paper electrode. Glucose and ethanol sensitivities of the enzyme electrode material were determined in the manner previously described using a 2 mm disc of electrode material at an applied potential of 280 mV: 10mM Glucose 0.2% v/v ethanol Current output (µA) 7.0 0.1 These figures again demonstrate the high substrate sensitivity, and low alcohol (ethanol) sensitivity, obtained using platinum oxide containing resin bonded carbon paper enzyme electrodes.

Claims: An enzyme electrode of the type comprising a) an electrically conductive support member comprising a porous, electrically conductive layer of resin-bonded carbon or graphite particles having dispersed throughout said layer and in intimate contact with said carbon or graphite particles, finely-divided particles of or containing a platinum group metal, said carbon or graphite particles and said platinum group metal or metal-containing particles being bonded together by a synthetic resin into a heterogeneous, porous substrate layer consisting essentially of resin-bonded carbon or graphite particles having said platinum group metal or metal-containing particles distributed uniformly throughout said layer and b) an enzyme immobilised or adsorbed onto the surface of said porous layer, said electrode being amperometrically responsive to the activity of said enzyme when the electrode is immersed at an applied fixed potential in a liquid sample containing a substrate for the enzyme, characterised in that said metal or metal-containing particles are either i) particles consisting entirely of platinum oxide, or ii) particles of platinum that have been oxidised to provide a surface film of platinum oxide on the surface of the particles. An enzyme electrode according to claim 1, wherein the binder is a hydrophobic synthetic resin. An enzyme electrode according to claim 1 or 2, wherein the synthetic resin binder is a fluorocarbon resin. An enzyme electrode according to claim 3, wherein the synthetic resin binder is polytetrafluoroethylene. An enzyme electrode according to any one of claims 1 to 4, wherein the particles of finely divided platinum oxide or finely divided oxidised platinum metal are preadsorbed onto the surface of the finely divided particles of carbon or graphite, prior to the bonding of said finely divided carbon or graphite particles to form said layer. An enzyme electrode according to any one of claims 1 to 5, wherein said heterogeneous layer of resin-bonded carbon or graphite particles contains finely divided platinum particles, the surface of which has been anodised to provide a thin oxide film thereon. An enzyme electrode according to any one of claims 1 to 6, wherein the enzyme immobilised or adsorbed onto the surface of the substrate is an oxido-reductase. An enzyme electrode according to claim 7, wherein the oxido-reductase is glucose oxidase. An enzyme electrode according to any one of claims 1 to 8, wherein said heterogeneous layer of resin-bonded carbon or graphite particles comprising said finely divided platinum oxide, or said oxidised particles of platinum, is provided as a porous surface layer bonded to an underlying support member. An enzyme electrode according to claim 9, wherein said underlying support member is electrically conductive. An enzyme electrode according to claim 10, wherein the electrically conductive support member is an electrically conductive carbon paper. An enzyme electrode according to any one of claims 1 to 11, the surface of which is protected by a microporous membrane permeable to said substrate. An enzyme electrode according to claim 12, wherein said membrane is a polycarbonate membrane. A method of reducing the alcohol sensitivity of enzyme electrodes of the type comprising an enzyme immobilised or adsorbed onto the surface of an electrically conductive support member consisting of or comprising a porous layer of resin-bonded carbon or graphite particles, said particles having intimately mixed therewith, or deposited or adsorbed onto the surface of the individual particles prior to bonding to form said layer, finely divided platinum, thereby to form a porous, substrate layer onto which said enzyme is adsorbed or immobilised and comprising a substantially heterogeneous layer of resin-bonded carbon or graphite particles, with said finely divided platinum dispersed substantially uniformly throughout said layer, which comprises subjecting the particles of finely divided platinum to an anodisation treatment, before or after incorporation into the electrode, thereby to provide said particles with an anodised surface. A method according to claim 14, wherein said finely divided platinum particles are anodised after incorporation thereof into said porous layer and before or after immobilisation thereon of said enzyme. A method according to claim 15, wherein said anodisation is effected by subjecting the electrically conductive support member comprising said particles incorporated thereon in said porous layer, to a polarisation treatment. A method according to claim 16, wherein said anodisation treatment comprises subjecting the electrically conductive support member comprising said particles, to a polarisation at a potential of from +1 to +2 volts with reference to a silver/silver chloride electrode for a period of from 1 to 30 minutes. A method according to claim 16, wherein the polarisation treatment is effected at a potential of about +1.5 volts with reference to a silver/silver chloride electrode. A method according to claim 16, wherein said polarisation treatment comprises exposing the electrode to cyclical polarisation at potentials of about ±2 volts with reference to a silver/silver chloride reference electrode for a period of from 1 to 30 minutes. A method according to claim 19, wherein said cyclical polarisation treatment is effected over the range ±1.5 volts with reference to a silver/silver chloride reference electrode.

Inventors: MULLEN WILLIAM HENRY, MULLEN, WILLIAM, HENRY
Applicants: CAMBRIDGE LIFE SCIENCES, CAMBRIDGE LIFE SCIENCES PLC
Application year: 1988
Main classification: C12M1
IPC codes: C12Q1, G01N27, C12N11