EP1311849A2 - Detecteur d'hemoglobine - Google Patents

Detecteur d'hemoglobine

Info

Publication number
EP1311849A2
EP1311849A2 EP01953454A EP01953454A EP1311849A2 EP 1311849 A2 EP1311849 A2 EP 1311849A2 EP 01953454 A EP01953454 A EP 01953454A EP 01953454 A EP01953454 A EP 01953454A EP 1311849 A2 EP1311849 A2 EP 1311849A2
Authority
EP
European Patent Office
Prior art keywords
electrode
hemoglobin
sensing chamber
sample
reagent
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.)
Ceased
Application number
EP01953454A
Other languages
German (de)
English (en)
Inventor
Alastair Hodges
Ron Chatelier
Thomas Beck
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
LifeScan Inc
Original Assignee
USF Filtration and Separations Group Inc
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Priority claimed from US09/616,512 external-priority patent/US6632349B1/en
Priority claimed from US09/615,691 external-priority patent/US6638415B1/en
Priority claimed from US09/616,556 external-priority patent/US6444115B1/en
Application filed by USF Filtration and Separations Group Inc filed Critical USF Filtration and Separations Group Inc
Publication of EP1311849A2 publication Critical patent/EP1311849A2/fr
Ceased legal-status Critical Current

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
    • 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
    • C12Q1/004—Enzyme electrodes mediator-assisted
    • 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
    • C12Q1/005—Enzyme electrodes involving specific analytes or enzymes
    • C12Q1/006—Enzyme electrodes involving specific analytes or enzymes for glucose
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
    • G01N33/84—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving inorganic compounds or pH

Definitions

  • the present invention relates to a device and method for measuring the level of hemoglobin in a blood sample.
  • the device comprises a disposable electrochemical cell containing an agent which lyses red blood cells and a reagent capable of being reduced by hemoglobin.
  • Hemoglobin is a respiratory molecule found in red blood cells. It is responsible for transporting oxygen from the lungs to body cells and for transporting carbon dioxide from body cells to the lungs. Hemoglobin has a molecular weight of 68,000 and contains four polypeptide chains. Each chain binds to a heme group which consists of a tetrapyrrole ring chelated to an Fe *2 ion. In the lungs, the iron atoms of the hemoglobin molecule reversibly combine with an oxygen molecule, which is then transported to body cells as blood circulates. The oxygen is released from the hemoglobin molecule in the tissues, then the oxygen-free hemoglobin molecule picks up carbon dioxide which is transported back to the lungs, where it is released.
  • Hemoglobin is produced in cells in the bone marrow that become red blood cells. Certain illnesses result in a deficiency of hemoglobin, such as anemia and sickle cell disease. Still other diseases, such as polycythemia or erythrocytosis, result in excessive levels of hemoglobin. Therefore, as an aid in the diagnosis or monitoring of such diseases, a method and device for determining the concentration of hemoglobin in whole blood is desirable.
  • Numerous methods and devices for the determination of hemoglobin are known. These methods include both direct analysis, i.e., analysis without prior modification of the hemoglobin, and indirect analysis.
  • An example of a direct analysis method is the Tallquist Method, wherein a measurement of the transmission or reflection optical density of the red color imparted by oxyhemoglobin, one form of hemoglobin, is obtained.
  • An example of an indirect analysis method is Drabkin's Method. In this method, the iron in hemoglobin is oxidized with a ferricyanide to form methemoglobin, which is converted with a cyanide to c ⁇ anmethemoglobin, which is then measured spectrometrically. Both of these methods have the disadvantage of requiring expensive analytical instrumentation and complicated sample preparation. Therefore, a quick, simple, and inexpensive device and method for measuring hemoglobin that overcomes the deficiencies of prior art methods is desirable.
  • a device and method are provided for measuring hemoglobin with a disposable sensing element, suitable for a single use, that can be combined with a meter to give a robust, fast, and easy to use test that is amenable to field as well as laboratory use.
  • an electrochemical sensor is provided that utilizes a redox agent that reacts with hemoglobin to produce an electrochemically detectable signal.
  • the method of preferred embodiments measures total hemoglobin, oxygenated plus unoxygenated, in contrast to spectrophotometric methods wherein the hemoglobin is converted to a single form in a separate chemical step, e.g., oxidation of hemoglobin containing Fe +2 to methemoglobin containing Fe +3 .
  • a device for detecting a presence or an absence of hemoglobin in an aqueous sample including an electrochemical cell having a sensing chamber, a first electrode, a second electrode, an aperture for admitting the sample into the sensing chamber, and a reagent contained within the sensing chamber wherein the reagent is capable of being reduced by hemoglobin to generate an electrical signal indicative of the presence or absence of hemoglobin.
  • the electrochemical cell may be designed to be disposed of after use in a single experiment.
  • first electrode is a sensing electrode.
  • the sensing electrode may be platinum, palladium, carbon, indium oxide, tin oxide, gold, iridiu , copper, steel, silver, or mixtures thereof.
  • the first electrode may be formed by a technique including sputtering, vapor coating, screen printing, thermal evaporation, ink jet printing, ultrasonic spraying, slot coating, gravure printing or lithography.
  • the second electrode is a counter electrode.
  • the second electrode may be a metal in contact with a metal salt, for example, silver in contact with silver chloride, silver in contact with silver bromide, silver in contact with silver iodide, mercury in contact with mercurous chloride, and mercury in contact with mercurous sulfate.
  • the second electrode may also be a reference electrode.
  • the electrochemical cell further includes a third electrode, which may be a reference electrode.
  • the third electrode may include a metal in contact with a metal salt, for example, silver in contact with silver chloride, silver in contact with silver bromide, silver in contact with silver iodide, mercury in contact with mercurous chloride, and mercury in contact with mercurous sulfate.
  • a metal salt for example, silver in contact with silver chloride, silver in contact with silver bromide, silver in contact with silver iodide, mercury in contact with mercurous chloride, and mercury in contact with mercurous sulfate.
  • the reagent may include dichromate, vanadium oxides, permanganate, eiectroactive organometallic complexes, quinones, dichlorophenoiindophenol, and ferricyanide.
  • a buffer such as a phosphate, carbonate, alkali metal salt of mellitic acid, or alkali metal salt of citric acid, may be contained within the sensing chamber.
  • the sensing chamber further includes a red blood cell lysing agent, for example, one selected from ionic detergents, nonionic detergents, proteolytic enzymes, lipases, saponin, sodium dodecyl sulfate, cetyl trimethylammo ⁇ ium bromide, or polyethoxylated octylphenol.
  • a red blood cell lysing agent for example, one selected from ionic detergents, nonionic detergents, proteolytic enzymes, lipases, saponin, sodium dodecyl sulfate, cetyl trimethylammo ⁇ ium bromide, or polyethoxylated octylphenol.
  • the sample includes whole blood.
  • the sensing chamber further includes a support contained within the sensing chamber, for example, mesh, nonwoven sheet, fibrous filler, macroporous membrane, sintered powder, or combinations thereof.
  • the reagent, red blood cell lysing agent, and/or buffer may be contained within or supported on the support.
  • the second electrode is mounted in opposing relationship a distance of less than about 500 microns from the first electrode; less than about 150 microns from the first electrode; or less than about 150 microns and greater than about 50 microns from the first electrode.
  • the device includes an interface for communication with a meter.
  • the interface may communicate a voltage or a current.
  • the electrochemical cell may be a thin layer electrochemical cell.
  • a method for detecting a presence or an absence of hemoglobin in an aqueous sample including providing a device including an electrochemical cell having a sensing chamber, a first electrode, a second electrode, an aperture for admitting the sample into the sensing chamber, and a reagent contained within the sensing chamber, wherein the reagent is capable of being reduced by hemoglobin to generate an electrical signal indicative of the presence or absence of hemoglobin; providing an aqueous sample; allowing the sample to flow through the aperture and into the sensing chamber, such that the first and second electrodes are substantially covered; and obtaining an electrochemical measurement indicative of the presence or absence of hemoglobin present in the sample.
  • the electrochemical cell is designed to be disposed of after use in a single experiment, or may be a thin layer electrochemical cell.
  • the electrochemical measurement may be an amperometric measurement, a potentiometric measurement, a coulometric measurement, or a quantitative measurement.
  • a method for measuring hemoglobin in a fluid whole blood sample, the whole blood sample containing red blood cells, the red blood cells containing hemoglobin, wherein the method includes providing a device including an electrochemical cell having a sensing chamber, a first electrode, a second electrode, an aperture for admitting the sample into the sensing chamber; a reagent contained within the sensing chamber and capable of being reduced by hemoglobin; and a red blood cell lysing agent contained within the sensing chamber; placing the whole blood sample in the sensing chamber, whereby the lysing agent contained within the sensing chamber releases hemoglobin from the red blood cells, whereby the hemoglobin thus released reduces the reagent; and obtaining an electrochemical measurement indicative of the level of hemoglobin present in the whole blood sample.
  • the electrochemical cell is designed to be disposed of after use in a single experiment, or may be a thin layer electrochemical cell.
  • the method further includes obtaining an electrochemical measurement indicative of the presence or absence of hemoglobin in the sample by applying a negative potential to the first electrode; measuring a current generated by reaction of the reagent and hemoglobin; analyzing the current to give a result, the result including a time required for substantial lysis of the red blood cells or a derived final value for the current; calculating a percentage of the reaction completed as a function of time based on the result of the analyzing step; reversing the potential on the first electrode; measuring a transient current; and determining a diffusion coefficient and a concentration of a reduced form of the reagent based on the transient current.
  • a method of manufacture of a device for detecting the presence or absence of hemoglobin in an aqueous sample including an electrochemical cell having a sensing chamber, a first electrode, a second electrode, an aperture for admitting the sample into the sensing chamber, and a reagent contained within the sensing chamber, and wherein the reagent is capable of being reduced by hemoglobin to generate an electrical signal indicative of the presence or absence of hemoglobin, the method including forming an aperture extending through a sheet of electrically resistive material, the aperture defining a side wall of the sensing chamber; mounting a first layer having a first electrode to a first side of the sheet and extending over the aperture whereby to define a first sensing chamber end wall, the first electrode facing the first side of the sheet; mounting a second layer having a second electrode to a second side of the sheet and extending over the aperture whereby to define a second sensing chamber end wall in substantial overlying registration with the first layer, the second electrode facing the second side of
  • the method further includes the step of providing a vent in the strip to permit the escape of air displaced from the sensing chamber as sample fills the sensing chamber.
  • the aperture is of a rectangular cross-section.
  • at least one of the electrodes includes a noble metal, such as palladium, platinum, and silver. At least one of the electrodes may be a sputter coated metal deposit. The electrodes may be adhered to the sheet, for example, by an adhesive such as a heat activated adhesive, pressure sensitive adhesive, heat cured adhesive, chemically cured adhesive, hot melt adhesive, and hot flow adhesive.
  • the method may include the step of providing a buffer and/or a red blood cell lysing agent contained within the sensing chamber.
  • the reagent and/or buffer may be printed onto at least one wall of the sensing chamber.
  • a support contained within the sensing chamber may also be provided, such as mesh, fibrous filler, macroporous membrane, sintered powder, or combinations thereof.
  • the reagent may be supported on or contained within the support.
  • At least the sheet or one of the layers includes a polymeric material selected from polyester, polystyrene, polycarbonate, polyolefin, and mixtures thereof, or polyethylene terephthalate.
  • the second electrode is mounted in opposing relationship a distance of less than about 500 microns from the first electrode; less than about 150 microns from the first electrode; or less than about 150 microns and greater than about 50 microns from the first electrode.
  • the electrochemical cell is designed to be disposed of after use in a single experiment.
  • FIG. 1 shows a plan view of an electrochemical cell.
  • FIG. 2 shows a cross-section view on line 10-10 of FIG. 1.
  • FIG. 3 shows an end-section view on line 11-11 of FIG. 1.
  • a method and device for measuring hemoglobin levels in a fluid whole blood sample is provided. If the whole blood sample is not in liquid form, i.e., dried blood, it can be analyzed after solid sample is mixed into a suitable fluid, e.g., water. Whole blood contained within a solid tissue sample may be analyzed after extraction using techniques well known in the art.
  • hemoglobin Prior to its analysis, hemoglobin is released from the red blood cells in which it is contained. This may be accomplished by pretreating the whole blood sample with a lysing agent prior to its introduction into the electrochemical cell. Alternatively, a lysing agent may be contained within the electrochemical cell itself. Other agents may also be used to pretreat the sample. For example, pH may be adjusted to a desired level by means of a buffer or neutralizing agent, or a substance that renders interfering species nonreactive may be added.
  • the electrochemical cell is preferably disposable and designed for use in a single experiment.
  • the electrochemical cell is a thin layer sensor such as that disclosed in U.S. 5,942,102 (incorporated herein by reference in its entirety).
  • a preferred embodiment of such an electrochemical cell is illustrated in FIGS. 1, 2, and 3.
  • the cell illustrated in FIGS. 1, 2, and 3 includes a polyester core 4 having a circular aperture 8.
  • Aperture 8 defines a cylindrical cell side wall 12.
  • Adhered to one side of core 4 is a polyester sheet 1 having a sputter coating of palladium 2. The sheet is adhered by means of an adhesive 3 to core 4 with palladium 2 adjacent core 4 and covering aperture 8.
  • a second polyester sheet 7 having a second sputter coating of palladium 6 is adhered by means of contact adhesive 5 to the other side of core 4 and covering aperture 8. There is thereby defined a cell having cylindrical side wall 12 closed on each end by palladium metal 2, 6.
  • the assembly is notched at 9 to provide for a solution to be admitted to the cell or to be drawn in by wicking or capillary action and to allow air to escape.
  • the metal films 2, 6 are connected with suitable electrical connections or formations whereby potentials may be applied and currently measured.
  • Such a thin layer electrochemical cell is prepared by first forming an aperture extending through a sheet of electrically resistive material, the aperture defining a side wall of the electrochemical cell.
  • Suitable electrically resistive materials which may be used in the sheet containing the aperture, or in other layers in the cell, include, for example, materials such as polyesters, polystyrenes, polycarbonates, polyolefins, polyethylene terephthalate, mixtures thereof, and the like.
  • the aperture in the sheet is rectangular, however other shapes, e.g., circular, may be used as well.
  • a first thin electrode layer is then mounted on one side of the sheet of electrically resistive material, extending over the aperture and forming an end wall.
  • the layer may be adhered to the sheet, for example, by means of an adhesive.
  • Suitable adhesives include, for example, heat activated adhesives, pressure sensitive adhesives, heat cured adhesives, chemically cured adhesives, hot melt adhesives, hot flow adhesives, and the like.
  • the electrode layer is prepared by coating (e.g., by sputter coating) a sheet of electrically resistive material with a suitable metal, for example, palladium.
  • a second thin electrode layer is then mounted on the opposite side of the electrically resistive material, also extending over the aperture, so as to form a second end wall.
  • the electrode layers are mounted in opposing relationship at a distance of less than about 1 millimeter, desirably less than about 800 microns, more desirably less that about 600, or preferably less than about 500 microns, more preferably less than about 300 to 150 microns, more preferably less than 150 microns, and most preferably between 25, 40, 50, 100 and 150 microns.
  • a second aperture or ingress is then provided for liquid to enter the cell. Such an ingress can be provided by forming a notch along one edge of the device which extends through the electrode layers and aperture.
  • the electrode layers are provided with connection means allowing the sensors to be placed in a measuring circuit.
  • Chemicals for use in the cell such as redox reagents, lysing agents, buffers, and other substances, may be supported on the cell electrodes or walls, on one or more independent supports contained within cell, or may be self supporting. If the chemicals are to be supported on the cell electrodes or walls, the chemicals may be applied by use of application techniques well known in the art, such as ink jet printing, screen printing, lithography, ultrasonic spraying, slot coating, gravure printing, and the like. Suitable independent supports may include, but are not limited to, meshes, nonwoven sheets, fibrous fillers, macroporous membranes, and sintered powders. The chemicals for use in the cell may be supported on or contained within a support.
  • the materials used within the cell as well as the materials used to construct the cell are in a form amenable to mass production, and the cells themselves are designed to be able to be used for a single experiment then disposed of.
  • a disposable cell is one that is inexpensive enough to produce that it is economically acceptable to be used only for a single test.
  • the cell may conveniently only be used for a single test. Inconveniently in this context means that steps such as washing and/or reloading of reagents would need to be taken to process the cell after a single use to render it suitable for a subsequent use.
  • the perceived value of the result of the test to the user is the same or greater than the cost of the cell to purchase and use, the cell purchase price being set by the cost of supplying the cell to the user plus an appropriate mark up.
  • the cells have relatively low materials costs and simple fabrication processes.
  • the electrode materials of the cells should be inexpensive, such as carbon, or be used in sufficiently small amounts such that expensive materials may be used. Screen printing carbon or silver ink is a process suitable for forming electrodes with relatively inexpensive materials.
  • electrode materials such as platinum, palladium, gold or iridium
  • methods with better material utilization, such as sputtering or evaporative vapor coating are more suitable as they may give extremely thin films.
  • the substrate materials for the disposable cells also are preferably inexpensive.
  • Examples of such inexpensive materials are polymers such as polyvinylchloride, polyimide, polyester and coated papers and cardboard.
  • Cell assembly methods also are preferably amenable to mass production. These methods include fabricating multiple cells on cards and separating the card into individual strips subsequent to the main assembly steps, and web fabrication where the cells are produced on a continuous web, which is subsequently separated into individual strips.
  • Card processes are most suitable when close spatial registration of multiple features is required for the fabrication and/or when stiff cell substrate materials are to be used.
  • Web processes are most suitable when the down web registration of features is not as critical and flexible webs may be used.
  • the convenient single use requirement for the disposable cell is desirable so that users are not tempted to try to reuse the cell and possibly obtain an inaccurate test result.
  • the single use requirement for the cell may be stated in user instructions accompanying the cell.
  • the cell may also be fabricated such that using the cell more than once is difficult or not possible. This may be accomplished, for example, by including reagents that are washed away or consumed during the first test and so are not functional in a second test.
  • the signal of the test may be examined for indications that reagents in the cell have already reacted, such as an abnormally high initial signal, and the test aborted.
  • Another method includes providing a means for breaking electrical connections in the cell after the first test in a cell has been completed.
  • the Electrodes At least one of the electrodes in the cell is a sensing electrode, defined as an electrode sensitive to the amount of oxidized redox agent.
  • a sensing electrode defined as an electrode sensitive to the amount of oxidized redox agent.
  • a second electrode acting as reference electrode is present which acts to provide a reference potential.
  • At least one other electrode is present which functions as a counter electrode to complete the electrical circuit.
  • This second electrode may also function as a reference electrode.
  • a separate electrode may perform the function of a reference electrode.
  • Materials suitable for the sensing, counter, and reference electrodes are compatible with the redox reagents present in the device. Compatible materials will not react chemically with the redox reagent or any other substance present in the cell. Examples of such suitable materials include, but are not limited to, platinum, palladium, carbon, indium oxide, tin oxide, mixed indium/tin oxides, gold, silver, iridium and mixtures thereof. These materials may be formed into electrode structures by any suitable method, for example, by sputtering, vapor coating, screen printing, thermal evaporation or lithography. In preferred embodiments, the material is sputtered or screen printed to form the electrode structures.
  • Non-limiting examples of materials suitable for use in the reference electrode include metal/metal salt systems such as silver in contact with silver chloride, silver bromide or silver iodide, and mercury in contact mercurous chloride or mercurous sulfate.
  • the metal may be deposited by any suitable method and then brought into contact with the appropriate metal salt. Suitable methods include, for example, electrolysis in a suitable salt solution or chemical oxidation.
  • Such metal/metal salt systems provide better potential control in potentiometric measurement methods than do single metal component systems.
  • the metal/metal salt electrode systems are used as a separate reference electrode in an amperometric sensor.
  • Suitable red blood cell lysing agents include detergents, both ionic and non-ionic, proteolytic enzymes, and lipases.
  • Suitable ionic detergents include, for example, sodium dodecyl sulfate and cetyl trimethylammonium bromide.
  • proteolytic enzymes include trypsin, chymotrypsin, pepsin, papain, and Pronase E, a very active enzyme having broad specificity.
  • Nonionic surfactants suitable for use include, e.g., ethoxylated octylphenols, including the Triton X Series available from Rohm & Haas of Philadelphia, Pennsylvania.
  • saponins i.e., plant glycosides that foam in water, are used as the lysing agent.
  • Suitable redox reagents include those which are capable of oxidizing hemoglobin.
  • redox reagents suitable for use in analyzing hemoglobin include, but are not limited, to salts of ferricyanide, dichromate, vanadium oxides, permanganate, and eiectroactive organometallic complexes.
  • Organic redox reagents such as dichlorophenoiindophenol, and quinones are also suitable.
  • the redox reagent for analyzing hemoglobin is ferricyanide.
  • a buffer may be present along with the redox reagent in dried form in the electrochemical cell. If a buffer is used, it is present in an amount such that the resulting pH level is suitable for adjusting the oxidizing potential of the redox reagent to a level suitable for oxidizing hemoglobin but not other species that it is not desired to detect.
  • the buffer is present in a sufficient amount so as to substantially maintain the pH of the sample at the desired level during the test.
  • buffers suitable for use include phosphates, carbonates, alkali metal salts of mellitic acid, and alkali metal salts of citric acid. The choice of buffer will depend on the desired pH. The buffer is selected so as not to react with the redox reagent.
  • redox reagents and buffers other substances may also be present within the electrochemical cell.
  • substances include, for example, viscosity enhancers and low molecular weight polymers.
  • Hydrophilic substances may also be contained within the cell, such as polyethylene glycol, polyacr ⁇ lic acid, dextran, and surfactants such as those marketed by Rohm & Haas Company of Philadelphia, Pennsylvania, under the trade name TritonTM or by ICI Americas Inc. of Wilmington, Delaware, under the trade name TweenTM.
  • Such substances may enhance the fill rate of the cell, provide a more stable measurement, and inhibit evaporation in small volume samples.
  • the sample In measuring hemoglobin present in a whole blood sample, the sample is introduced into the sensor cell, whereupon the sample dissolves the dried reagents and other substances present in the sensor cell. If the sample has not been pretreated with a lysing agent, a lysing agent present in the sensor cell releases hemoglobin from the red blood cells. The redox reagent then reacts with hemoglobin present in the sample to form the reduced form of the redox reagent. In the case of a potentiometric sensor, the resulting ratio of oxidized to reduced form of the redox reagent fixes the potential of the sensing electrode relative to the reference electrode. This potential is then used as a measure of the concentration of the hemoglobin originally in the sample.
  • the sensing cell is operated as an amperometric sensor.
  • the reduced redox reagent formed by reaction with hemoglobin is electrochemically oxidized at the sensing electrode. The current resulting from this electrochemical reaction is then used to measure the concentration of hemoglobin originally in the sample.
  • the sensor is operated in potentiometric or coulometric mode.
  • the cell's electrodes are used to produce an electrical signal, i.e., a voltage or current, readable by an attached meter.
  • an interface for connecting the cell to the meter is provided.
  • the meter may display the measurement in a visual, audio or other form, or may store the measurement in electronic form.
  • a typical concentration of hemoglobin e.g., 14 g/dL, would yield a ferrocyanide concentration of 8.2 mM upon oxidation.
  • the minimum detectable limit in a preferred embodiment of the method and device is approximately 0.1 mM.
  • substantially complete lysis of all red blood cells is achieved before measurement of hemoglobin.
  • a rapid hemoglobin measurement may be obtained even if the lysis step proceeds slowly by using a first and second potential application step.
  • a sensor configuration as described above is used, e.g., a sensor wherein the bottom electrode is palladium, upon which the dried reagents are deposited, and wherein the top electrode is a gold electrode.
  • the first potential is applied by applying a -0.3 V potential at zero time to set the gold electrode as the working electrode.
  • the increase in current can be used in a number of ways: to assess the time required for full lysis and reaction, to extrapolate the signal to longer times, or to assess the fraction of hemoglobin reacted at a given time.
  • the first method gives some quality assurance, and the second and third methods yield a shorter test.
  • the potential can be reversed to +0.3 V and the reverse transient current can be measured and analyzed using electrochemical methods known in the art, e.g., as disclosed in U.S. Application No. 08/981385 filed April 17, 1998, and U.S. 5,942,102 (both incorporated herein by reference in their entirety), to calculate the diffusion coefficient and concentration of ferrocyanide.
  • the first potential application may also be used to subtract i ⁇ terferents. The ferricyanide reacts more quickly with interfering substances which are free in the plasma than with hemoglobin which is packaged in red blood cells.
  • the ratio of the minimum to maximum (or extrapolated) currents resulting from the first potential application may be used to yield the concentration of reduced mediator measured by the second potential pulse (at +0.3 V), thereby yielding a more accurate, corrected concentration of hemoglobin.
  • the simplest correction would be:
  • [Hb]' [Hb] * (1 - imin/imax) wherein [Hb]' is the corrected concentration of hemoglobin, [Hb] is the uncorrected concentration of hemoglobin, imin is the measured current and imax is the extrapolated current resulting from the first potential application.
  • Information relating to the rate of a chemical reaction that yields at least one eiectroactive product can be obtained using the sensor by ensuring that the chemical reaction is localized at a site remote from the electrode used to electrochemically react the eiectroactive product(s).
  • the site of the chemical reaction is sufficiently removed from the electrode such that the mass transfer of the eiectroactive species from the chemical reaction site to the electrode effectively controls the current flowing at the electrode at any time.
  • This arrangement ensures a substantially linear eiectroactive species concentration gradient between the chemical reaction site and the electrode.
  • the concentration of the eiectroactive species is maintained at effectively zero at the electrode by the electrochemical reaction taking place there.
  • the time course of the magnitude of this concentration gradient will therefore be substantially determined only by the time course of the concentration of the eiectroactive specie(s) at the chemical reaction site and the diffusion coefficient(s) of the eiectroactive reaction product(s) in the liquid medium.
  • the time course of this current will reflect the time course of the chemical reaction occurring at the remote site. This allows the current measured at the electrode (or charge passed if the current is integrated) to be a used as a convenient measure of the rate and extent of the chemical reaction taking place.
  • An example of a suitable method for ensuring that the chemical reaction is remote from the working electrode is to immobilize one or more of the reaction components on a solid surface remote from the electrode.
  • the reaction component(s) can be immobilized by incorporating them in a polymeric matrix that is dried on or otherwise attached to the solid surface.
  • reaction component(s) can also be tethered directly to the solid surface either by chemical or physical bonding. Alternatively one or more of the reaction components can simply be dried onto the solid surface without special immobilization means. In this situation one or more of the reaction components is sufficiently low in mobility, in the liquid matrix filling the electrochemical cell, that it does not migrate substantially from the position where it was dried during the time period that the electrochemical current can be usefully monitored to perform the required measurement. In this context substantial migration means that the slowest moving component required for the chemical reaction approaches closely enough to the working electrode that Cottrell type depletion kinetics begin to effect the time course of the current flowing at the electrode.
  • the range of separation distance between the chemical reaction site and the working electrode in preferred embodiments is desirably less than about 1 cm, preferably less than 5 mm, more preferably between 5, 10, 50, 100, 200, 500 microns and 5 mm, more preferably between 5, 10, 50, 100, 200 and 500 microns, and most preferably between 5, 10, 50, 100 and 200 microns.
  • a counter electrode in contact with the liquid sample is provided to complete the electrochemical circuit.
  • the counter electrode can function as a combined counter/reference electrode or a separate reference electrode can be provided.
  • the working electrode and counter electrode are desirably spaced apart at a distance greater than about 300 microns, preferably at a distance greater than about 500 microns, more preferably at a distance between about 500 microns and 10 mm, more preferably at a distance between about 500 microns and 1, 2, 5 mm, and most preferably between 1 mm and 2, 5, 10 mm.
  • the working electrode is constructed of materials that do not react chemically with any component with which it will come into contact during use to an extent that interferes with the current response of the electrode. If the working electrode is to be used as an anode then examples of suitable materials are platinum, palladium, carbon, carbon in combination with inert binders, iridium, indium oxide, tin oxide, mixtures of indium and tin oxide. If the working electrode is to be used as a cathode then in addition to the material listed above other suitable materials are steel, stainless steel, copper, nickel, silver and chromium.
  • Examples of materials suitable for the counter electrode are platinum, palladium, carbon, carbon in combination with inert binders, iridium, indium oxide, tin oxide, mixture of indium and tin oxide, steel, stainless steel, copper, nickel, chromium, silver and silver coated with a substantially insoluble silver salt such as silver chloride, silver bromide, silver iodide, silver ferrocyanide, silver ferricyanide.
  • the site of the chemical reaction can be localized on a bare wall or on the counter electrode, remote from the working electrode.
  • the site of the chemical reaction can be on the same plane as the working electrode or more preferably in a plane facing and substantially parallel to the working electrode.
  • a sensor suitable for use with certain embodiments includes a working electrode and a counter electrode which are disposed on an electrically insulating substrate. On a second substrate is disposed a layer of chemical reactants, where at least one of the reactants is substantially immobilized on the substrate. In use, the space between walls of the sensor is filled with a liquid containing a substance which is capable of reacting with the reagents to produce at least one eiectroactive species.
  • the products of the chemical reaction diffuse towards the working electrode where the eiectroactive specie(s) are electrochemically reacted to produce a current.
  • the magnitude of the current or the charge passed at a particular time, or the time course of the current or charge passed can then be used to obtain a measure of the rate or extent of the chemical reaction occurring at the reactant layer.
  • the reactants are disposed on the counter electrode which is disposed on an electrically resistive substrate.
  • the materials of construction of the counter electrode are inert to reaction with any of the components of the reactants disposed on the electrode.
  • the method of obtaining an electrochemical measurement described above may be applied to any suitable electrochemical system, including hemoglobin.
  • An example of the method as applied to a typical, albeit different, electrochemical system is measuring glucose in whole blood using the enzyme PQQ dependent glucose dehydrogenase (GDHpqq) and a redox mediator. In this reaction glucose in the blood reacts with GDHpqq to form gluconic acid. In the process, the PQQ in the enzyme is reduced.
  • a mediator such as potassium ferricyanide
  • the enzyme in the oxidized form can then react with further glucose.
  • the net effect of this reaction is to produce two ferrocyanide molecules for each glucose molecule reacted.
  • Ferrocyanide is an eiectroactive species, and so can be oxidized at an electrode to produce a current.
  • Other suitable enzymes for this reaction are glucose oxidase (GOD) or NAD dependent glucose dehydrogenase.
  • GOD glucose oxidase
  • lactate dehydrogenase and alcohol dehydrogenase may be used.
  • Other suitable redox mediators include ferrocinium, osmium complexes with bipyridine, and benzophenone.
  • the reaction of glucose in whole blood with the enzyme can be slow, taking up to a few minutes to go to completion. Also, the higher the haematocrit of the blood sample, the slower the reaction.
  • the haematocrit of the blood is the volume fraction of red cells in the whole blood sample. For example, a solution containing 50 mg/ml GDHpqq, 0.9 M potassium ferricyanide and 50 mM buffer at pH 6.5 was deposited on the counter electrode and the water removed to leave a dried reactant layer. In this layer the GDHpqq is large enough to be effectively immobilized on the counter electrode, whereas the ferricyanide can mix more evenly throughout the liquid in the electrochemical cell.
  • the blood sample was introduced into the cell and a potential of +300 mV immediately applied between the working electrode and the counter electrode.
  • a potential of +300 mV is most preferred for oxidizing ferrocyanide, the potential is desirably between +40 mV and +600 mV, preferably between +50 mV and +500 mV, and more preferably between +200 mV and +400 mV.
  • the working electrode consisted of a layer of gold sputtered onto a polyester substrate and the counter electrode consisted of a layer of palladium sputtered onto a polyester substrate.
  • the average di/dt was 3.82, 2.14 and 1.32 microamps/second, respectively.
  • the diffusion coefficients of ferrocyanide for these samples were 2.0 x 10 ⁇ , 1.7 x 10 '6 and 1.4 x 10 '6 cm 2 /sec for 20%, 42%, and 65% haematocrit samples, respectively.
  • the electrode area was 0.1238 cm 2 and L was 125 microns. These values yield reaction rates of 2.0, 1.3, and 0.99 mM/second for the 20%, 42%, and 65% haematocrit samples, respectively.
  • the method as described above for measuring the reaction of glucose in blood may be suitably modified to apply to other electrochemical systems, including hemoglobin, as will be appreciated by one skilled in the art.

Landscapes

  • Chemical & Material Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Organic Chemistry (AREA)
  • Immunology (AREA)
  • General Health & Medical Sciences (AREA)
  • Analytical Chemistry (AREA)
  • Zoology (AREA)
  • Molecular Biology (AREA)
  • Wood Science & Technology (AREA)
  • Proteomics, Peptides & Aminoacids (AREA)
  • Biochemistry (AREA)
  • Physics & Mathematics (AREA)
  • Biotechnology (AREA)
  • Microbiology (AREA)
  • Genetics & Genomics (AREA)
  • Hematology (AREA)
  • Biomedical Technology (AREA)
  • General Physics & Mathematics (AREA)
  • Pathology (AREA)
  • Biophysics (AREA)
  • General Engineering & Computer Science (AREA)
  • Bioinformatics & Cheminformatics (AREA)
  • Urology & Nephrology (AREA)
  • Food Science & Technology (AREA)
  • Inorganic Chemistry (AREA)
  • Medicinal Chemistry (AREA)
  • Cell Biology (AREA)
  • Emergency Medicine (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Electrochemistry (AREA)
  • Investigating Or Analysing Biological Materials (AREA)
  • Apparatus Associated With Microorganisms And Enzymes (AREA)
  • Investigating Or Analyzing Non-Biological Materials By The Use Of Chemical Means (AREA)
  • Measuring Or Testing Involving Enzymes Or Micro-Organisms (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

La présente invention concerne un dispositif et un procédé pour mesurer l'hémoglobine dans un échantillon de fluide. Ce dispositif comprend une cellule électrochimique jetable, telle qu'une cellule électrochimique en couche mince (1), contenant un réactif qui peut être réduit par l'hémoglobine. Selon cette invention, un échantillon de fluide convenable pouvant être analysé consiste en du sang total. Si l'hémoglobine devant être analysée est présente dans des globules rouges, un agent de lyse peut être ajouté à l'échantillon, afin de libérer l'hémoglobine avant l'analyse.
EP01953454A 2000-07-14 2001-07-12 Detecteur d'hemoglobine Ceased EP1311849A2 (fr)

Applications Claiming Priority (9)

Application Number Priority Date Filing Date Title
US61643300A 2000-07-14 2000-07-14
US09/616,512 US6632349B1 (en) 1996-11-15 2000-07-14 Hemoglobin sensor
US09/615,691 US6638415B1 (en) 1995-11-16 2000-07-14 Antioxidant sensor
US615691 2000-07-14
US09/616,556 US6444115B1 (en) 2000-07-14 2000-07-14 Electrochemical method for measuring chemical reaction rates
US616433 2000-07-14
US616512 2000-07-14
US616556 2000-07-14
PCT/US2001/021964 WO2002006828A2 (fr) 2000-07-14 2001-07-12 Detecteur d'hemoglobine

Publications (1)

Publication Number Publication Date
EP1311849A2 true EP1311849A2 (fr) 2003-05-21

Family

ID=27505127

Family Applications (4)

Application Number Title Priority Date Filing Date
EP01952446A Expired - Lifetime EP1303758B1 (fr) 2000-07-14 2001-07-06 Procede electrochimique pour mesurer des vitesses de reactions chimiques
EP01954660A Withdrawn EP1301780A2 (fr) 2000-07-14 2001-07-12 Detecteur d'antioxydant
EP01953454A Ceased EP1311849A2 (fr) 2000-07-14 2001-07-12 Detecteur d'hemoglobine
EP01961641A Ceased EP1315967A2 (fr) 2000-07-14 2001-07-13 Immunodetecteur

Family Applications Before (2)

Application Number Title Priority Date Filing Date
EP01952446A Expired - Lifetime EP1303758B1 (fr) 2000-07-14 2001-07-06 Procede electrochimique pour mesurer des vitesses de reactions chimiques
EP01954660A Withdrawn EP1301780A2 (fr) 2000-07-14 2001-07-12 Detecteur d'antioxydant

Family Applications After (1)

Application Number Title Priority Date Filing Date
EP01961641A Ceased EP1315967A2 (fr) 2000-07-14 2001-07-13 Immunodetecteur

Country Status (19)

Country Link
EP (4) EP1303758B1 (fr)
JP (3) JP4948737B2 (fr)
KR (5) KR20030038664A (fr)
CN (4) CN1441902A (fr)
AR (1) AR029723A1 (fr)
AT (1) ATE349695T1 (fr)
AU (6) AU2001273197B2 (fr)
CA (4) CA2416207C (fr)
CZ (2) CZ2003409A3 (fr)
DE (1) DE60125544T2 (fr)
ES (1) ES2277933T3 (fr)
HK (1) HK1055147A1 (fr)
IL (4) IL153583A0 (fr)
MX (2) MXPA03000382A (fr)
NO (2) NO20030017L (fr)
PL (2) PL359335A1 (fr)
SG (2) SG140463A1 (fr)
TW (1) TWI238890B (fr)
WO (4) WO2002006788A2 (fr)

Families Citing this family (65)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6413410B1 (en) 1996-06-19 2002-07-02 Lifescan, Inc. Electrochemical cell
AUPN661995A0 (en) 1995-11-16 1995-12-07 Memtec America Corporation Electrochemical cell 2
AUPO581397A0 (en) 1997-03-21 1997-04-17 Memtec America Corporation Sensor connection means
US6294281B1 (en) 1998-06-17 2001-09-25 Therasense, Inc. Biological fuel cell and method
US7005273B2 (en) 2001-05-16 2006-02-28 Therasense, Inc. Method for the determination of glycated hemoglobin
GB0130684D0 (en) 2001-12-21 2002-02-06 Oxford Biosensors Ltd Micro-band electrode
US20060134713A1 (en) 2002-03-21 2006-06-22 Lifescan, Inc. Biosensor apparatus and methods of use
US20030180814A1 (en) * 2002-03-21 2003-09-25 Alastair Hodges Direct immunosensor assay
US7368190B2 (en) 2002-05-02 2008-05-06 Abbott Diabetes Care Inc. Miniature biological fuel cell that is operational under physiological conditions, and associated devices and methods
RU2235998C2 (ru) * 2002-11-14 2004-09-10 Уральский государственный экономический университет Способ определения оксидантной/антиоксидантной активности растворов
US7473264B2 (en) 2003-03-28 2009-01-06 Lifescan, Inc. Integrated lance and strip for analyte measurement
US20040193202A1 (en) 2003-03-28 2004-09-30 Allen John J. Integrated lance and strip for analyte measurement
US7699967B2 (en) 2003-06-19 2010-04-20 Arkray, Inc. Analysis implement with opening in insulation film
US7999003B2 (en) * 2003-08-26 2011-08-16 Mannatech, Incorporated Antioxidant compositions and methods thereto
US7723099B2 (en) * 2003-09-10 2010-05-25 Abbott Point Of Care Inc. Immunoassay device with immuno-reference electrode
CA2511746C (fr) 2003-11-06 2013-03-26 Lifescan, Inc. Stylo d'administration de medicament a organe de notification d'evenement
EP3059580A1 (fr) * 2004-05-21 2016-08-24 Agamatrix, Inc. Dispositif de cellules électrochimiques pour mesure électrochimique
US20050284773A1 (en) 2004-06-29 2005-12-29 Allen John J Method of preventing reuse in an analyte measuring system
CN1323296C (zh) * 2004-07-05 2007-06-27 江苏省肿瘤医院 硅烷交联壳聚糖膜基的流动注射化学发光免疫检测池及制备方法
RU2384832C2 (ru) * 2005-01-21 2010-03-20 Михаил Евгеньевич Гиваргизов Подложка для реализации метода комплексных действий с материалами, способ ее изготовления, способ изготовления материалов на подложке и устройства для работы с ней
CN1858613B (zh) * 2005-05-08 2010-08-11 王宏栋 锂离子电池材料测试方法与测试装置
TW200706650A (en) 2005-08-11 2007-02-16 Toyo Boseki A substrate specificity improved composition for glucose measurement
GB0524770D0 (en) * 2005-12-03 2006-01-11 Univ Bristol A low cost water test device for use in developing countries in remote field conditions
EP1797817A1 (fr) * 2005-12-19 2007-06-20 F.Hoffmann-La Roche Ag Capteur de type sandwich pour la détermination de la concentration des analytes
ES2326286T3 (es) 2005-12-19 2009-10-06 F. Hoffmann-La Roche Ag Sensor tipo sandwich para determinar la concentracion de un analito.
US8409864B2 (en) * 2006-01-06 2013-04-02 Renal Solutions, Inc. Ammonia sensor and system for use
EP2035836B1 (fr) * 2006-07-03 2013-02-27 Thermo Finnigan LLC Dispositif pour le traitement de sang total en vue de la détection d'un analyte
RU2482495C2 (ru) * 2006-10-12 2013-05-20 Конинклейке Филипс Электроникс Н.В. Быстрый биосенсор со слоем реагента
CN1975373B (zh) * 2006-12-12 2010-11-10 西安交通大学 一种测定液固反应速率的装置及方法
TWI516601B (zh) * 2007-10-26 2016-01-11 環球生物醫療感測器私人有限公司 電化學檢測之裝置及方法
EP2257803A4 (fr) 2008-03-11 2012-04-25 Urobiologics Llc Activité de réduction/oxydation de l'urine maternelle comme indicateur de caractéristiques liées au sexe d'un f tus
US8759109B2 (en) 2008-03-11 2014-06-24 Urobiologics Llc Use of female mammal's urine for determination of fetal gender related characteristics
US10996218B2 (en) 2008-03-11 2021-05-04 Ournextbaby Llc Methods for chemotaxis / redox driven separation of X and Y chromosome bearing sperm and their insemination in gender specific menstrual cycles
CA2730544C (fr) 2008-07-11 2017-08-29 Universal Biosensors Pty Ltd Capteur ameliore pour test immunologique
BRPI0914373A2 (pt) * 2008-10-14 2015-10-20 Piramal Healthcare Ltd "método eletroquímico não-enzimático para determinação simultânea de hemoglobina total e hemoglibina glicosilada"
GB0820817D0 (en) * 2008-11-13 2008-12-24 Wireless Biodevices Ltd Electrode, electrochemical sensor and apparatus, and methods for operating the same
US20100213057A1 (en) 2009-02-26 2010-08-26 Benjamin Feldman Self-Powered Analyte Sensor
CN102395880A (zh) 2009-04-17 2012-03-28 环球生物医疗感测仪私人有限公司 电化学机载控制侦测
EP2459730B1 (fr) 2009-07-27 2016-12-07 Suresensors LTD Perfectionnements apportés à des dispositifs de détection
US20110048972A1 (en) * 2009-08-31 2011-03-03 Lifescan Scotland Limited Multi-analyte test strip with shared counter/reference electrode and inline electrode configuration
US20110079522A1 (en) * 2009-10-02 2011-04-07 Lifescan Scotland Limited Multi-analyte test strip with inline working electrodes and shared opposing counter/reference electrode
IL209760A (en) * 2009-12-11 2015-05-31 Lifescan Scotland Ltd A system and method for measuring filling is satisfactory
FR2956904B1 (fr) * 2010-03-01 2012-12-14 Eumed Biotechnology Co Ltd Procede de determination de substances oxydantes et reductrices dans un aliment, echantillon d'analyse et dispositif de mesure pour ce procede
CA2823180C (fr) 2010-12-31 2018-10-23 Ronald C. Chatelier Systemes et procedes pour une mesure d'analyte tres precise
CN102288694B (zh) * 2011-07-04 2015-04-01 北京泰克美高新技术有限公司 一种易氧化物质的检测装置及方法
CN102507688B (zh) * 2011-10-13 2014-03-12 中国科学院化学研究所 电化学生物传感器及其制备方法与应用
CN102507715A (zh) * 2011-11-14 2012-06-20 湖南省湘电试验研究院有限公司 一种电力用油抗氧化剂的检测方法
CN104380091B (zh) 2012-06-28 2016-06-22 西门子医疗保健诊断公司 信号放大的读出器设备和方法
JP6036212B2 (ja) * 2012-11-20 2016-11-30 ニプロ株式会社 ヘモグロビン測定装置およびヘモグロビン測定方法
JP2014102144A (ja) * 2012-11-20 2014-06-05 Nipro Corp 糖化ヘモグロビン測定キットおよび糖化ヘモグロビン測定方法
GB2509325B (en) * 2012-12-28 2014-12-10 Lifescan Scotland Ltd End-fill electrochemical-based analytical test strip with perpendicular intersecting sample-receiving chambers
GB2514846B (en) * 2013-06-07 2015-09-30 Lifescan Scotland Ltd Electrochemical-based analytical test strip with a soluble electrochemically-active coating opposite a bare electrode
CN103344617B (zh) * 2013-06-17 2015-05-06 重庆大学 光激活单分子荧光生物化学反应动力学显微镜及试验方法
US9453812B2 (en) 2014-06-24 2016-09-27 Lifescan Scotland Limited End-fill electrochemical-based analytical test strip with perpendicular intersecting sample-receiving chambers
WO2016038526A1 (fr) * 2014-09-08 2016-03-17 Indian Institute Of Science Dispositif et procédé de détection de l'hémoglobine et ses complexes
US20170324119A1 (en) * 2016-05-06 2017-11-09 GM Global Technology Operations LLC Reference electrode implementation with reduced measurement artifacts
KR102451440B1 (ko) 2016-06-15 2022-10-05 이스트만 케미칼 컴파니 물리적 증착된 바이오센서 컴포넌트
CN106483182A (zh) * 2016-08-22 2017-03-08 浙江大学 一种干式测定血红蛋白的生物传感器及其制备方法
KR102547063B1 (ko) 2016-09-16 2023-06-22 이스트만 케미칼 컴파니 물리적 증착에 의해 제조된 바이오센서 전극
JP7111698B2 (ja) 2016-09-16 2022-08-02 イーストマン ケミカル カンパニー 物理蒸着によって製造されるバイオセンサー電極
KR102646492B1 (ko) * 2017-06-22 2024-03-12 이스트만 케미칼 컴파니 물리적으로 증착된 전기화학 센서용 전극
RU2711410C1 (ru) * 2019-03-13 2020-01-17 Федеральное государственное автономное образовательное учреждение высшего образования "Уральский федеральный университет имени первого Президента России Б.Н. Ельцина" Способ потенциометрического определения антиоксидантной емкости раствора
WO2021064466A1 (fr) * 2019-09-30 2021-04-08 Universal Biosensors Pty Ltd Capteur électrochimique pour l'analyse de boissons
WO2023014366A1 (fr) * 2021-08-05 2023-02-09 Hewlett-Packard Development Company, L.P. Puits de test possédant un fond muni d'une seule ouverture
EP4355852A1 (fr) * 2021-08-05 2024-04-24 Hewlett-Packard Development Company, L.P. Puits d'essai de réaction en chaîne de la polymérase comprenant une partie magnétique

Family Cites Families (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CA1219040A (fr) * 1983-05-05 1987-03-10 Elliot V. Plotkin Mesure de reactions catalysees par des enzymes
US5141868A (en) * 1984-06-13 1992-08-25 Internationale Octrooi Maatschappij "Octropa" Bv Device for use in chemical test procedures
US4859583A (en) * 1985-02-25 1989-08-22 Amoco Corporation Chemiluminescent immunochemical technique for low molecular weight antigens
CN2059997U (zh) * 1990-02-12 1990-08-01 王文理 数字式血红蛋白测量仪
US5071527A (en) * 1990-06-29 1991-12-10 University Of Dayton Complete oil analysis technique
US5239258A (en) * 1992-04-03 1993-08-24 University Of Dayton Freshness and stability test using oxidative degradation
US5427912A (en) * 1993-08-27 1995-06-27 Boehringer Mannheim Corporation Electrochemical enzymatic complementation immunoassay
AUPM506894A0 (en) * 1994-04-14 1994-05-05 Memtec Limited Novel electrochemical cells
AUPN363995A0 (en) * 1995-06-19 1995-07-13 Memtec Limited Electrochemical cell
AUPP238898A0 (en) * 1998-03-12 1998-04-09 Usf Filtration And Separations Group Inc. Heated electrochemical cell
AUPN661995A0 (en) * 1995-11-16 1995-12-07 Memtec America Corporation Electrochemical cell 2
AUPO585797A0 (en) * 1997-03-25 1997-04-24 Memtec America Corporation Improved electrochemical cell
US6054039A (en) * 1997-08-18 2000-04-25 Shieh; Paul Determination of glycoprotein and glycosylated hemoglobin in blood
EP0990154A1 (fr) * 1998-04-15 2000-04-05 Biofutura S.R.L. Appareil con u pour effectuer plusieurs tests sur des echantillons de vins ou similaires
WO1999063346A1 (fr) * 1998-06-01 1999-12-09 Roche Diagnostics Corporation Procede et dispositif d'immunoessai electrochimique de plusieurs analytes
JP2001050926A (ja) * 1999-08-06 2001-02-23 Sankyo Co Ltd バイオセンサ

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See references of WO0206828A2 *

Also Published As

Publication number Publication date
KR20030036609A (ko) 2003-05-09
NO20030017D0 (no) 2003-01-02
KR100828450B1 (ko) 2008-05-13
AU7688801A (en) 2002-01-30
JP2004530099A (ja) 2004-09-30
EP1303758A2 (fr) 2003-04-23
IL153585A0 (en) 2003-07-06
IL153582A0 (en) 2003-07-06
CA2416249A1 (fr) 2002-01-24
JP4948737B2 (ja) 2012-06-06
WO2002006828A8 (fr) 2003-11-06
WO2002006806A3 (fr) 2002-10-17
SG138459A1 (en) 2008-01-28
CN1441902A (zh) 2003-09-10
CZ2003416A3 (cs) 2004-02-18
DE60125544D1 (de) 2007-02-08
KR20030036605A (ko) 2003-05-09
WO2002006828A3 (fr) 2002-08-15
NO20030027D0 (no) 2003-01-03
CN1441901A (zh) 2003-09-10
MXPA03000383A (es) 2004-09-13
AU2001276888B2 (en) 2006-03-16
CZ2003409A3 (cs) 2003-10-15
TWI238890B (en) 2005-09-01
AU2001275902A1 (en) 2002-01-30
CN1313822C (zh) 2007-05-02
NO20030027L (no) 2003-03-03
KR20080003941A (ko) 2008-01-08
WO2002006788A8 (fr) 2003-11-06
SG140463A1 (en) 2008-03-28
WO2002008763A3 (fr) 2002-06-13
CA2415602A1 (fr) 2002-01-31
CN1441903A (zh) 2003-09-10
WO2002006788A3 (fr) 2002-08-29
ATE349695T1 (de) 2007-01-15
AU7319701A (en) 2002-01-30
WO2002008763A2 (fr) 2002-01-31
IL153584A0 (en) 2003-07-06
KR100884501B1 (ko) 2009-02-18
EP1303758B1 (fr) 2006-12-27
KR20030038664A (ko) 2003-05-16
KR20030038665A (ko) 2003-05-16
CA2415342A1 (fr) 2002-01-24
JP2004504604A (ja) 2004-02-12
IL153583A0 (en) 2003-07-06
CA2416207A1 (fr) 2002-01-24
AU2001282890A1 (en) 2002-02-05
DE60125544T2 (de) 2007-10-04
CA2415602C (fr) 2012-04-10
PL359860A1 (en) 2004-09-06
MXPA03000382A (es) 2004-09-13
AR029723A1 (es) 2003-07-10
PL359335A1 (en) 2004-08-23
EP1315967A2 (fr) 2003-06-04
NO20030017L (no) 2003-03-13
CN1441905A (zh) 2003-09-10
CA2416207C (fr) 2011-08-30
ES2277933T3 (es) 2007-08-01
HK1055147A1 (en) 2003-12-24
WO2002006806A2 (fr) 2002-01-24
CN1252471C (zh) 2006-04-19
WO2002006788A2 (fr) 2002-01-24
AU2001273197B2 (en) 2006-05-25
WO2002006828A2 (fr) 2002-01-24
EP1301780A2 (fr) 2003-04-16
JP2004504597A (ja) 2004-02-12

Similar Documents

Publication Publication Date Title
US6632349B1 (en) Hemoglobin sensor
WO2002006828A2 (fr) Detecteur d'hemoglobine
US6444115B1 (en) Electrochemical method for measuring chemical reaction rates
EP0406304B1 (fr) Procede et appareil d'analyse diagnostique amperometrique
US8801907B2 (en) Electrochemical cell
US6638415B1 (en) Antioxidant sensor
AU2001276888A1 (en) Antioxidant sensor
KR100628860B1 (ko) 전기화학 센서
US20030159944A1 (en) Apparatus for amperometric diagnostic anagnostic analysis
AU2001273197A2 (en) Electrochemical method for measuring chemical reaction rates
AU2001273197A1 (en) Electrochemical method for measuring chemical reaction rates
EP1729119A1 (fr) Système de test
RU2271536C2 (ru) Способ измерения количества гемоглобина
IL153582A (en) Hemoglobin sensor
AU2006203606B2 (en) Electrochemical method for measuring chemical reaction rates
AU2007209797B2 (en) Electrochemical method for measuring chemical reaction rates

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

17P Request for examination filed

Effective date: 20030213

AK Designated contracting states

Designated state(s): AT BE CH CY DE DK ES FI FR GB GR IE IT LI LU MC NL PT SE TR

AX Request for extension of the european patent

Extension state: AL LT LV MK RO SI

RAP1 Party data changed (applicant data changed or rights of an application transferred)

Owner name: LIFESCAN, INC.

17Q First examination report despatched

Effective date: 20050318

17Q First examination report despatched

Effective date: 20050318

17Q First examination report despatched

Effective date: 20050318

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE APPLICATION HAS BEEN REFUSED

18R Application refused

Effective date: 20090625

REG Reference to a national code

Ref country code: HK

Ref legal event code: WD

Ref document number: 1056215

Country of ref document: HK