US 20060219551 A1
Disclosed is an electrochemical sensor for the determination of analytes in body fluids, e.g. glucose in blood. The sensor involves a non-conductive base which provides a flow path for the body fluid with the base having a working and counter electrode on its surface which are in electrical communication with a detector of current. The base and a cover therefore provide a capillary space containing the electrodes into which the body fluid is drawn by capillary action. The counter electrode has a sub-element which contains an electroactive material and is configured in the system (sensor and meter) to provide an error signal when insufficient body fluid is drawn into the capillary.
11. An electrochemical test sensor for detecting the concentration of an analyte in a fluid test sample, the test sensor comprising:
a non-conductive base that provides a flow path for the fluid test sample, the base including a counter electrode, a working electrode and a sub-element on an upper surface thereof, the counter and working electrodes being adapted to be in electrical communication with a detector of electrical current, the sub-element being physically disconnected from the counter electrode, the sub-element comprising an electroactive material that is adapted to allow oxidation to occur at the surface of the working electrode under an applied potential;
a reaction layer on at least the surface of the working electrode, the reaction layer comprising an enzyme; and
a cover coupled with the non-conductive base and forming a capillary space with an opening for the introduction of the fluid test sample thereto, the space forming a flow path for the fluid test sample,
wherein the sub-element of the counter electrode is located upstream from the working electrode relative to the opening such that when electrochemical communication occurs between only the sub-element and the working electrode there is insufficient flow of electrical current through a detector to constitute a valid determination of the analyte concentration in the fluid test sample.
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24. An electrochemical test sensor adapted to assist in determining the concentration of an analyte in a fluid test sample, the test sensor comprising:
a base assisting in forming an opening for introducing the fluid test sample;
a working electrode being coupled to the base;
a counter electrode being coupled to the base, the counter electrode and the working electrode being adapted to be in electrical communication with a detector of electrical current, a portion of the counter electrode being located downstream relative to the opening and at least a portion of the working electrode; and
a sub-element being coupled to the base, the sub-element being physically disconnected from the counter electrode, the sub-element comprising an electroactive material that is adapted to allow oxidation to occur at the surface of the working electrode under an applied potential, the sub-element of the counter electrode being located upstream from the working electrode relative to the opening such that when electrochemical communication occurs between only the sub-element and the working electrode there is insufficient flow of electrical current through a detector to constitute a valid determination of the analyte concentration in the fluid test sample.
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33. A method of determining whether a sufficient quantity of a fluid test sample has been introduced to an electrochemical test sensor, the method comprising the acts of:
providing the electrochemical test sensor adapted to assist in determining the concentration of an analyte in a fluid test sample, the sensor comprising a base, a working electrode, a counter electrode and a sub-element, the base assisting in forming an opening for introducing the fluid test sample, the working electrode being coupled to the base, the counter electrode being coupled to the base, the counter electrode and the working electrode being adapted to be in electrical communication with a detector of electrical current, at least a portion of the counter electrode being located downstream relative to the opening and at least a portion of the working electrode, the sub-element being coupled to the base, the sub-element being physically disconnected from the counter electrode, the sub-element comprising an electroactive material that is adapted to allow oxidation to occur at the surface of the working electrode under an applied potential, the sub-element of the counter electrode being located upstream from the working electrode relative to the opening such that when electrochemical communication occurs between only the sub-element and the working electrode there is insufficient flow of electrical current through a detector to constitute a valid determination of the analyte concentration in the fluid test sample;
introducing the fluid test sample to the test sensor; and
determining whether a sufficient quantity of the fluid test sample has been introduced and, if not, notifying a user that an insufficient quantity of the fluid test sample has been introduced.
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This is a continuation application of U.S. Ser. No. 10/382,170, filed Mar. 4, 2003, now pending.
The present invention relates to an electrochemical biosensor which can be used for the determination of analytes such as glucose in blood. Electrochemical biosensors of the type under consideration are disclosed in U.S. Pat. Nos. 5,120,420 and 5,798,031. These devices have an insulating base upon which carbon electrodes are printed and are then covered with a reagent layer comprising a hydrophilic material in combination with an oxidoreductase specific for the analyte. These devices typically involve a base and a cover which are separated by a generally U-shaped piece as a spacer element or, in the case of the '031 patent, use an embossed cover, so that when the base and cover are mated there is created a capillary space containing the electrodes and the reagent layer. A hydrophilic polymer, e.g. carboxymethyl cellulose or poly(ethylene oxide) is used to facilitate the drawing of the aqueous test fluid into the capillary space.
In either embodiment, working and counter electrodes are screen printed onto the base so that an electrochemically created current can flow when these electrodes are electrically connected and a potential is created between them. Touching the opening in the end of the sensor to a drop of test fluid such as blood results in the fluid being drawn into the capillary space, so that it covers the reaction layer on the surface of the electrode. An enzymatic reaction between the oxidoreductase and the analyte creates a flow of electrons which are carried to the working electrode by a mediator such as ferricyanide and flow through the working electrode to a meter which measures the magnitude of the flow. The counter electrode serves dual purposes. First, it provides a fixed potential against which the working electrode is controlled. Second, for a two electrode system, such as that depicted in the drawings, the counter electrode is used to complete the electrical circuit. In this mode, each electron that is transferred to the working electrode is returned to the test fluid at the counter electrode side of the cell. The device's software is programmed to correlate the magnitude of this flow with the concentration of analyte in the test sample. In order for this current to flow, a complete circuit is formed by covering both electrodes with the conductive fluid test sample and applying a potential therebetween.
A problem which is sometimes associated with this type of sensor occurs when an insufficient amount of blood is applied to the opening, so that the working and counter electrodes are not completely covered with the sample. This results in an incomplete current flowing across the electrodes, and, since the amount of analyte detected is directly proportional to the current flowing through the detection meter, failure to completely cover the sensor's electrodes can result in an artificially low reading of the sample's analyte concentration. One technique for dealing with this under filling problem is discussed in U.S. Pat. No. 5,628,890 which involves a mechanism for preventing any response from being detected when the sample volume is too low to provide an accurate reading.
In co-pending application Ser. No. 09/731,943 there is disclosed an electrochemical sensor of the type described above in which a small sub-element of the non-working electrode is positioned upstream from the working electrode, so that when there is insufficient flow of electrical current through the detector to constitute a valid test for the concentration of analyte in the fluid test sample, the pre-programmed detector causes the emission of an error signal to alert the user of the device that the test result should be disregarded. This is achievable because there is generated an altered current profile in the event that the capillary space of the sensor is underfilled. However, in this device, the tripping current carried by the straight carbon sub-element requires some time to reach the necessary potential thereby increasing the duration of the test.
The present invention is an improvement to an electrochemical sensor for determining the concentration of an analyte in a fluid test sample, e.g. glucose in blood. The sensor comprises:
The construction of the electrochemical sensor with which the present invention is concerned is illustrated by
In the drawing, this sub-element 40 a is a discrete unit, but it could form a continuous trace to the conductive leads (38). The electrode pattern to which 39 is the working electrode and 40 is the counter electrode is produced next. The electrodes are covered with an insulating (dielectric) pattern 42 with a slot 41 to expose the sub-element to the reaction layer 44. The function of the reaction layer is to convert glucose, or other analyte in the fluid test sample, stoichiometrically into a chemical species which is electrochemically measurable in terms of an electrode pattern produced by the components of the electrode pattern. The reaction layer typically contains an enzyme which reacts with the analyte to produce mobile electrons, and an electron acceptor (mediator) such as ferricyanide to carry the mobile electrons to the surface of the working electrode. The enzyme in the reaction layer can be combined with a hydrophilic polymer such as carboxymethylcellulose or poly(ethylene oxide). The two parts, 39 and 40, of the electrode print provide the working 39 and counter 40 electrodes necessary for the electrochemical determination of the analyte which is the crux of the present invention. The working and counter electrodes are configured in a manner such that the major portion of the counter electrode is located downstream (in terms of the direction of the fluid flow along the flow path) from the forward portion of the working electrode 40. This configuration offers the advantage of allowing the test fluid to completely cover the exposed portion of the working electrode for all cases in which an undetected partial fill has occurred. However, sub-element 40 a of the counter electrode is positioned upstream from the forward element of the working electrode 39, so that when an inadequate amount of fluid test sample to completely cover the working electrode enters the capillary space, there will be formed an electrical connection between counter electrode sub-element 40 a and the exposed portion of the upper part of the working electrode due to the conductivity of the fluid sample, e.g. blood. By programming the current detector to give an error signal when the current profile it receives is below certain pre-determined levels, the sensor system can be designed to actively advise the user that insufficient blood has entered the sensor's cavity and that another test for analyte concentration should be conducted. The system is designed to give an error signal in the case of a short fill by generating a current profile when the capillary space is underfilled which is different from that which is obtained when there is complete filling of the capillary space. However, it was found that this design requires more time than is desirable to activate the assay, which delay may be caused by a lower initial current being generated by the electrodes. It has now been discovered that this delay can be shortened or eliminated by printing the sub-element of the counter electrode with an ink which comprises an electroactive material with the electroactive material being present in an amount which is insufficient to maintain the flow of electrons through the detector to constitute a valid determination of analyte concentration. Conversely, the sub-element is designed to allow a sufficient flow of electrons through the detector to start the timing sequence of the instrument.
The term electroactive material is intended to mean material which is sufficiently positive to allow oxidation to occur at the working electrode under the applied potential. Suitable electroactive materials include AgO or other electropositive metal oxide such as, for example, the oxide of Cu, Mn, Pb, Hg, Ni, Co, Bi, Re or Te or compounds made from these metals. Other classes of electropositive materials which can be used are oxides of metals including those mentioned above and halides of such metals. A metal capable of forming an electropositive metal oxide such as by auto oxidation can be applied to the sub-element of the counter electrode and then oxidized in place to form the metal oxide.
The only requirement of the electropositive material is as stated above. Accordingly, compounds of an electropositive metal such as AgCl can be used since the Ag can be converted to the AgCl species upon contact of the sub-element with a fluid test sample such as plasma or whole blood which contains chloride. This embodiment offers the advantage of not requiring a secondary operation to form the silver oxide layer on the electrode's surface.
The sensor of the present invention is constructed using several screen printing passes using inks of various compositions. The ink for the first pass comprises a material which is of sufficiently low resistance to serve as the conductive leads (38) and contains the electropositive material that forms the sub-element of the counter electrode (40 a) as shown in
While the particular dimensions of the electrodes are not critical, the area of the sub-element of the counter electrode is typically less than that of the working electrode. This element is made as small as possible in view of the restraints of the screen printing process. The area which is exposed to the fluid test sample can be made even smaller by printing the dielectric layer 42, so that only a very small portion (2% to 7% of the area of the working electrode) is exposed to provide the sub-element of the counter electrode. In one embodiment, reaction layer 44 can be denied contact with the sub-element 40 a of the counter electrode by providing a screen that does not allow printing of reagent ink over the counter electrode sub-element 40 a and serves the purpose of starving the sub-element for reagent thereby not allowing it to function as a proper counter electrode. This is preferred, so that an error condition is achieved in the case of failure of the test fluid to contact the bulk of the counter electrode 40.
While sub-element 40 a is depicted as being physically disconnected from the rest of the conductive leads (38) in the drawing, it can be physically connected to them forming one continuous path on the counter electrode side. In the embodiment where the sub-element is physically disconnected from the main body of the counter electrode, it is provided with its own connection to the detector through the main body of the counter electrode.
The two parts 39 and 40 of the printed electrodes provide the working and counter electrodes necessary for the electrochemical determination of the analyte. The electrode ink, which is about 14 μm thick, typically contains electrochemically active carbon. Components of the conductor ink are preferably a mixture of carbon and silver which is chosen to provide a path of low electrical resistance between the electrodes and the detector with which they are in operative connection via contact with the conductive pattern at the fish-tail end 45 of the type of sensor depicted in the drawing. The counter electrode can be comprised of silver/silver chloride in which case it will function more like a reference electrode. The function of the dielectric pattern 42 is to insulate the electrodes from the fluid test sample except in a defined area near the center of the electrode patterns to enhance the reproducibility of the detector reading. A defined area is important in this type of electrochemical determination because the measured current is dependent both on the concentration of the analyte and the area of the reaction layer which is exposed to the analyte containing test sample. A typical dielectric layer 42 comprises a UV cured acrylic modified polymethane which is about 10μ thick.
The present invention is further illustrated by the following examples:
The sensor is constructed using various layers of polymer thick film (PTF) to form the working sensor. The conductive leads and trigger subunit is printed from any standard conductive PTF utilizing a metal pigment for high conductivity. In this case, a thermoplastic silver/graphite PTF was used for its cost advantage and cured in an air furnace. The working and counter electrodes were printed using a standard carbon/graphite PTF and the area can be defined using a standard UV or conventional dielectric PTF. The curing of the PTF converts the silver to silver oxide on the PTF surface. Any remaining silver on the surface of the trigger sub-electrode is further converted using an oxygen plasma process that is currently used to improve the performance of the working electrode surface as disclosed in U.S. Pat. No. 5,429,735. This plasma process could also use a halide gas that can react with the metal to form a metal halide at the surface. Alternatively, any wet chemical reaction capable of oxidizing the silver could be used as long as it does not adversely affect the performance of the carbon/graphite electrode. The sensor is then printed with a proprietary reagent PTF to form the working base. The lid is then attached to form the working cell of the sensor.
The sensor can be constructed using various layers of PTF's where the trigger PTF has incorporated in it a metal oxide or metal halide. The advantage of this system is that it does not need to be converted to form the necessary electropositive material. In this example, a specialty PTF ink is made using AgO and graphite to form the conductive leads. This ink is screen printed as previously described except that the AgO is not formed during the subsequent air curing or O2 plasma treatment. The electrode and dielectric PTF is printed and cured as in Example I.
Other metal oxides can be used in the manufacture of the PTF, but depending on the conductivity of the oxide it may not function as well for the conducting leads, so that a separate print from the conductive leads would be required. This would increase the cost of manufacturing the sensor due to the need for an additional printing layer.
A base stock, typically of polycarbonate, is printed with various inks to form the electrodes 39 and 40 and then overcoated with a dielectric layer 42 in a predetermined pattern designed to leave a desired surface of the electrode exposed to contact by the fluid test sample as it enters the space formed by mating the lid 46 and the base 36. The particular configuration of the dielectric layer 42 is as depicted in
Two sensors having trigger electrodes as in
Carbon Trigger Electrode
A polycarbonate base was printed using DuPont 5085 Ag/graphite conductive PTF ink and cured using either a standard forced air tunnel or an IR tunnel oven to form the conductive leads 38. The electrodes 39, 40 and 40 a were then printed using DuPont 7102T PTF ink. This ink can be cured using either the forced air tunnel or an IR tunnel oven. A dielectric ink was applied to define the working, reference and trigger electrode area. The sensor was then subjected to an O2 plasma treatment to enhance the electrode surfaces.
In this embodiment, the sensor was produced in the same manner as that with the carbon trigger except that the trigger electrode 40 a was printed with the Ag/graphite PTF ink along with the conductive leads 38.
The air curing of the DuPont PTF inks (5085 and 7102T) converted the Ag at the surface of the trigger electrode to AgO. The O2 plasma used to enhance the electrode efficiency further oxidized any residual Ag at the surface of the trigger electrode.
These sensors were tested by determining the time required for the counter electrode subunit to reach the tripping current. The meter required that a minimum threshold current be obtained in order to start the timing sequence of the test. In a complete fill situation, the mediator is on the surface of the counter electrode and conversion of the glucose begins immediately to produce a current exceeding the threshold current. In an underfill condition, the mediator is situated several thousandths of an inch away from the trigger electrode. As the conversion of glucose occurs, the mediator must diffuse to the trigger electrode to produce the threshold current needed to start the meter timing sequence. The AgO or other electropositive species has a higher potential than the carbon and, therefore, the time required to render the threshold current is reduced. The trigger electrode is not large enough to carry the full burden of the reaction and is, therefore, not suitable as the counter electrode. The meter is preprogrammed with algorithms which monitor the current profile to detect an underfill condition and give the user an error signal. The result, termed countdown efficiency, was calculated inoculating the sensor with a known volume of blood (1.0 and 1.5 μL in this case) to produce an underfill condition. These volumes, through experimentation, have been determined to partially or fully cover the working electrode. The time required from sample inoculation until the meter starts its countdown was measured as countdown efficiency.
From the data presented in
For Ag/AgO at 1.0 μL, 70% of the tested sensors tripped immediately and another 30% tripped in less than 1 minute. At 1.5 μL, 100% of the sensors tripped immediately.
For carbon at 1.0 μL, 84% tripped in less than 1 minute and 16% never tripped until the meter errored out at 3 minutes. At 1.5 μL, 100% tripped within 1 minute.