WO2001057510A2 - Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations - Google Patents
Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations Download PDFInfo
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- WO2001057510A2 WO2001057510A2 PCT/US2001/002465 US0102465W WO0157510A2 WO 2001057510 A2 WO2001057510 A2 WO 2001057510A2 US 0102465 W US0102465 W US 0102465W WO 0157510 A2 WO0157510 A2 WO 0157510A2
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- Prior art keywords
- time
- concentration
- analyte
- preliminary
- hematocrit
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- 238000005534 hematocrit Methods 0.000 title claims abstract description 68
- 238000002848 electrochemical method Methods 0.000 title description 4
- 238000000034 method Methods 0.000 claims abstract description 55
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Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
- G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
- G01N27/28—Electrolytic cell components
- G01N27/30—Electrodes, e.g. test electrodes; Half-cells
- G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
- G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
- G01N27/3274—Corrective measures, e.g. error detection, compensation for temperature or hematocrit, calibration
-
- 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
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
-
- 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
- G01N33/66—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing involving blood sugars, e.g. galactose
Definitions
- the field of this invention is analyte determination, particularly electrochemical analyte determination and more particularly the electrochemical determination of blood analytes.
- Analyte detection in physiological fluids e g blood or blood derived products
- Analyte detection assays find use in a variety of applications, including clinical laboratory testing, home testing, etc., where the results of such testing play a prominent role in diagnosis and management in a variety of disease conditions
- Analytes of interest include glucose for diabetes management, cholesterol, and the like.
- analyte detection protocols and devices for both clinical and home use have been developed.
- an electrochemical method One type of method that is employed for analyte detection is an electrochemical method.
- an aqueous liquid sample is placed into a reaction zone in an electrochemical cell comprising two electrodes, i e a reference and working electrode, where the electrodes have an impedance which renders them suitable for amperometric measurement.
- the component to be analyzed is allowed to react directly with an electrode, or directly or indirectly with a redox reagent to form an oxidisable (or reducible) substance in an amount corresponding to the concentration of the component to be analyzed, i e. analyte
- the quantity of the oxidisable (or reducible) substance present is then estimated electrochemically and related to the amount of analyte present in the initial sample
- the hematocrit of the sample can be a source of analytical error in the ultimate analyte concentration measurement
- hematocrit can slow the equilibration chemistry in the electrochemical cell and/or slow the enzyme kinetics by increasing the sample viscosity in the cell, thereby attenuating the time current response and causing analytical error
- blood filte ⁇ ng membranes are employed to remove red blood cells and thereby minimize the hematoc ⁇ t effect
- Patent documents of interest include 5,942,102 and WO 97/18465
- the physiological sample is introduced into an electrochemical cell having a working and reference electrode
- a first elect ⁇ c potential is applied to the cell and the resultant cell current over a first pe ⁇ od of time is measured to determine a first time-current transient
- a second elect ⁇ c potential of opposite polarity is then applied to the cell and a second time-current transient is determined
- the preliminary concentration of the analyte (C 0 ) ⁇ s then calculated from the first and/or second time-current transients
- This preliminary analyte concentration, less a background value is then multiplied by a hematoc ⁇ t correction factor to obtain the analyte concentration in the sample, where the hematocrit correction factor is a function of the preliminary analyte concentration and the ratio of 2 current values ( ⁇ ) within the time-current transient of the electrochemical cell
- the subject methods and devices are suited for use m
- Methods and devices for determining the concentration of an analyte in a physiological sample are provided.
- the physiological sample is introduced into an electrochemical cell having a working and reference electrode.
- a first electric potential is applied to the cell and the resultant cell current over a first period of time is measured to determine a first time-current transient.
- a second electric potential of opposite polarity is then applied to the cell and a second a time-current transient is determined.
- the preliminary concentration of the analyte is then calculated from the first and/or second time-current transient.
- This preliminary analyte concentration, less a background value, is then multiplied by a hematocrit correction factor to obtain the analyte concentration in the sample, where the hematocrit correction factor is a function of the preliminary analyte concentration and the variable ⁇ of the electrochemical cell.
- the subject methods and devices are suited for use in the determination of a wide variety of analytes in a wide variety of samples, and are particularly suited for use in the determination of analytes in whole blood or derivatives thereof, where an analyte of particular interest is glucose.
- the subject methods will be described first followed by a review of a representative device for use in practicing the subject methods.
- the subject invention provides a method for determining a hematocrit corrected analyte concentration value in a physiological sample.
- hematocrit corrected analyte concentration is meant that the analyte concentration value determined using the subject methods has been modulated or changed to remove substantially all contribution of hematocrit to the value.
- the concentration value that is determined using the subject methods has been modified so that any contribution to the value from the hematocrit of the sample that would be present in the value but for the practicing of the subject methods is removed.
- the hematocrit signal is deconvoluted from the analyte signal in the subject methods, and only the analyte signal is employed in arriving at the final hematocrit corrected analyte concentration.
- the first step in the subject methods is to introduce a quantity of the physiological sample of interest into an electrochemical cell that includes spaced apart working and reference electrodes and a redox reagent system.
- the physiological sample may vary, but in many embodiments is generally whole blood or a derivative or fraction thereof, where whole blood is of particular interest in many embodiments.
- the amount of physiological sample, e.g. blood, that is introduced into the reaction area of the test strip varies, but generally ranges from about 0.1 to 10 ⁇ L, usually from about 0.9 to 1.6 ⁇ L.
- the sample is introduced into the reaction area using any convenient protocol, where the sample may be injected into the reaction area, allowed to wick into the reaction area, and the like, as may be convenient.
- the subject methods may be used, in principle, with any type of electrochemical cell having spaced apart working and reference electrodes and a redox reagent system
- the subject methods employ an electrochemical test strip.
- the electrochemical test strips employed in these embodiments of the subject invention are made up of two opposing metal electrodes separated by a thin spacer layer, where these components define a reaction area or zone in which is located a redox reagent system.
- the working and reference electrodes are generally configured in the form of elongated rectangular strips.
- the length of the electrodes ranges from about 1.9 to 4.5 cm, usually from about 2.0 to 2.8 cm.
- the width of the electrodes ranges from about 0.38 to 0.76 cm, usually from about 0.51 to 0.67 cm.
- the reference electrodes typically have a thickness ranging from about 10 to 100 nm and usually from about 10 to 20 nm.
- the length of one of the electrodes is shorter than the length of the other electrode, typically about 0.32 cm. The shorter electrode may be the working or reference electrode.
- the working and reference electrodes are further characterized in that at least the surface of the electrodes that faces the reaction area in the strip is a metal, where metals of interest include palladium, gold, platinum, silver, iridium, carbon, doped tin oxide, stainless steel and the like.
- the metal is gold or palladium.
- each of the electrodes is generally made up of an inert support material on the surface of which is present a thin layer of the metal component of the electrode.
- the thickness of the inert backing material typically ranges from about 51 to 356 ⁇ m, usually from about 102 to
- the thickness of the metal layer typically ranges from about 10 to 100 nm and usually from about 10 to 40 nm, e.g. a sputtered metal layer.
- Any convenient inert backing material may be employed in the subject electrodes, where typically the material is a rigid material that is capable of providing structural support to the electrode and, in turn, the electrochemical test strip as a whole. Suitable materials that may be employed as the backing substrate include plastics, e.g. PET, PETG, polyimide, polycarbonate, polystyrene, silicon, ceramic, glass, and the like.
- a feature of the electrochemical test strips used in these embodiments of the subject methods is that the working and reference electrodes as described above face each other and are separated by only a short distance, such that the distance between the working and reference electrode in the reaction zone or area of the electrochemical test strip is extremely small.
- This minimal spacing of the working and reference electrodes in the subject test strips is a result of the presence of a thin spacer layer positioned or sandwiched between the working and reference electrodes.
- the thickness of this spacer layer generally should be less than or equal to 500 ⁇ m, and usually ranges from about 102 to 153 ⁇ m.
- the spacer layer is cut so as to provide a reaction zone or area with at least an inlet port into the reaction zone, and generally an outlet port out of the reaction zone as well.
- the spacer layer may have a circular reaction area cut with side inlet and outlet vents or ports, or other configurations, e.g. square, triangular, rectangular, irregular shaped reaction areas, etc.
- the spacer layer may be fabricated from any convenient material, where representative suitable materials include PET, PETG, polyimide, polycarbonate, and the like, where the surfaces of the spacer layer may be treated so as to be adhesive with respect to their respective electrodes and thereby maintain the structure of the electrochemical test strip Of particular interest is the use of a die-cut double-sided adhesive st ⁇ p as the spacer layer
- the electrochemical test strips used in these embodiments of the subject invention include a reaction zone or area that is defined by the working electrode, the reference electrode and the spacer layer, where these elements are described above Specifically, the working and reference electrodes define the top and bottom of the reaction area, while the spacer layer defines the walls of the reaction area
- the volume of the reaction area is at least about 0 1 ⁇ L, usually at least about 1 ⁇ L and more usually at least about 1 5 ⁇ L, where the volume may be as large as 10 ⁇ L or larger
- the reaction area generally includes at least an inlet port, and in many embodiments also includes an outlet port
- the cross-sectional area of the inlet and outlet ports may vary as long as it is sufficiently large to provide an effective entrance or exit of fluid from the reaction area, but generally ranges from about 9 x lO ⁇ to 5 x 10 "3 cm 2 , usually from about 1 3 x 10 "3 to 2 5 x 10 "3 cm 2
- a redox reagent system which reagent system provides for the species that is measured by the electrode and therefore is used to derive the concentration of analyte in a physiological sample
- the redox reagent system present in the reaction area typically includes at least an enzyme(s) and a mediator
- the enzyme member(s) of the redox reagent system is an enzyme or plurality of enzymes that work in concert to oxidize the analyte of interest
- the enzyme component of the redox reagent system is made up of a single analyte oxidizing enzyme or a collection of two or more enzymes that work in concert to oxidize the analyte of interest
- Enzymes of interest include oxidases, dehydrogenases, upases, kinases, diphorases, quinoproteins, and the like
- the specific enzyme present in the reaction area depends on the particular analyte for which the electrochemical test strip is designed to detect, where representative enzymes include glucose oxidase, glucose dehydrogenase, cholesterol esterase, cholesterol oxidase, lipoprotein lipase, glycerol kinase, glycerol-3-phosphate oxidase, lactate oxidase, lactate dehydrogenase, pyruvate oxidase, alcohol oxidase, bilirubin oxidase, uricase, and the like
- the enzyme component of the redox reagent system is a glucose oxidizing enzyme, e g a glucose oxidase or glucose dehydrogenase
- the second component of the redox reagent system is a mediator component, which is made up of one or more mediator agents
- mediator agents include fer ⁇ cvanide, phenazine ethosulphate, phenazine methosulfate, pheylenediamine, 1 -methoxy-phenazine methosulfate, 2,6-d ⁇ methyl-l,4-benzoqu ⁇ none, 2,5- d ⁇ chloro-l,4-benzoqu ⁇ none, ferrocene derivatives, osmium bipy ⁇ dyl complexes, ruthenium complexes, and the like
- mediators of particular interest are fer ⁇ cyanide, and the like
- agents that mav be present include divalent cations such as calcium chloride, and magnesium chloride, pyrroloquinohne quinone, types of surfactants such as Triton, Macol, Tetronic, Silwet, Zonyl, and Pluronic, stabilizing agents such as albumin, sucrose, trehalose, manmtol, and lactose
- the redox reagent system is generally present in dry form
- the amounts of the va ⁇ ous components may vary, where the amount of enzyme component typically ranges from about 1 to 100 mg/mL, usually from about 5 to 80mg/mL, and the amount of mediator component typically ranges from about 5 to 1000 mM, usually from about 90 to 900 mM
- first and second time-current transients are obtained.
- the first and second time-current transients are obtained by applying a constant elect ⁇ c potential to the cell and observing the change in current over a pe ⁇ od of time in the cell
- first and second pulses are applied to the cell and the resultant time-current transients are observed
- the first time-current transient is obtained by applying a constant electric potential or first pulse to the cell, e g between the working and the reference electrodes, and observing the change in current over time between the electrodes, l e change in cell current, to obtain the first time-current transient
- the magmtude of the first applied electric potential generally ranges from about 0 to -0 6 N, usually from about -0 2 to -0 4 N
- the length of time over which the current between the electrodes is observed to obtain the first time-current transient typically ranges from about 3 to 20 seconds, usually from about 4 to 10 seconds
- the second time current is obtained by applying a second constant elect ⁇ c potential or second pulse, typically of opposite polarity from the first constant electric potential, to the electrodes and observing the change in current between the electrodes for a second period of time
- the magnitude of this second constant electric potential typically ranges from about 0 to +0 6 N, usually from about +0 2 to +0 4 N, where in many embodiments the magnitude of the second electric potential is the same as the magnitude of the first electric potential.
- the second time period typically ranges from about 1 to 10 seconds, usually from about 2 to 4 seconds.
- the overall time period required to obtain the requisite first and second time-current transients, as described above, is relatively short in certain embodiments.
- the total amount of time required to obtain the first and second time-current transients is less than about 30 seconds, usually less than about 20 seconds and more usually less than about 14 seconds.
- the next step in the subject methods is to use the observed first and second time- current transients, obtained as described above, to determine: (a) the variable ⁇ of the electrochemical cell used in the subject methods; and (b) a preliminary analyte concentration for the analyte of interest in the sample.
- the variable ⁇ employed in the subject methods is defined to describe the deviation of the electrochemical cell from ideality.
- ⁇ should approach unity under ideal conditions, i.e. reagent equilibration and glucose reaction are complete before the end of the first pulse. Any of these conditions not being complete will cause the ratio to deviate fron non-unity values.
- the denominator is defined as the average current over a short time period near the end of the first period of time, i.e. near the end of the application of the first electric potential or first pulse.
- the short period of time from which the average current is determined typically ranges from .2 to 2 seconds, usually from about .2 to 1.5 seconds and more usually from about .2 to 1.25 seconds, where in many embodiments the short period of time is about .3 second.
- the average current is determined at a time near the end of the first time period, typically within about 0.1 to 1 second,.
- the variable ⁇ is described by the formula: where: i ss is the steady-state current of the second applied electric potential; and i pP is the average current over a short period of time near the end of first time period, i.e. near the end of the time during which the first electric potential is applied to the cell.
- the average current may be the average current from 8.5 to 9.5 seconds of the 10 second long period, which is a 1.0 second time period 0.5 seconds from the end of the first time period
- the first and second time-current transients are also employed to derive a preliminary analyte concentration value for the sample being assayed.
- C o is the preliminary concentration of the analyte
- F is faraday's constant, i.e. 9.6485xl0 4 C/mol
- A is the area of the working electrode.
- the observed first and second time-current transients are used to determine the variable ⁇ of the electrochemical cell employed in the subject method and the preliminary concentration value of the analyte of interest in the assayed physiological sample.
- a hematocrit correction factor is determined, which hematocrit correction factor is used to obtain a hematocrit corrected analyte concentration value from the initial or preliminary analyte concentration value described above.
- the hematocrit correction factor is a factor with which the preliminary analyte concentration (typically less a background value) may be multiplied in order to obtain a hematocrit corrected analyte concentration value, i.e. a concentration value from which the hematocrit component has been removed.
- the hematocrit correction factor is a function of both the preliminary analyte concentration value and the variable ⁇ of the electrochemical cell.
- any hematocrit correction factor that can be multiplied by the preliminary concentration value (usually less a background value, as described in greater detail below) may be employed in the subject methods
- One class of hematocrit correction factors that find use in the subject methods are those that are derived from a three dimensional graph of C 0 , ⁇ and ⁇ (C 0 , ⁇ ) obtained from experimental data using a wide range of analyte and hematoc ⁇ t values
- hematocrit corrected concentration hematocrit correction factor x[ C 0 - ⁇ ] where ⁇ is the background value
- the above described methods yield a hematocrit corrected analyte concentration value, i e a concentration value in which the hematoc ⁇ t component has been deconvoluted and removed. As such, the above described methods provide for an accurate value of the concentration of the analyte in the sample being assayed.
- the subject meters are typically meters for amperometrically measuring the hematocrit corrected concentration of an analyte in a physiological sample.
- the subject meters typically include: (a) a means for applying a first electric potential to an electrochemical cell into which the sample has been introduced and measuring cell current as a function of time to obtain a first time-current transient; (b) a means for applying a second electric potential to the electrochemical cell and measuring cell current as a function of time to obtain a second time-current transient; (c) a means for determining a preliminary analyte concentration value and a variable ⁇ from said first and second time-currents; and (d) a means for removing the hematocrit component from the preliminary concentration value to derive the hematocrit corrected analyte concentration in said sample.
- Means (a) and (b) may be any suitable means, where representative means are described in WO 97/18465 and U.S. Patent No. 5,942,102; the disclosures of which are herein incorporated by reference.
- Means (c) and (d) are typically computing means present in the meter which are capable of using the measured first and second time current transients to ultimately obtain the hematocrit corrected analyte concentration.
- means (c) is typically a means that is capable of determining the preliminary concentration of the analyte of interest and the variable ⁇ from the first and second time-current transients using the equations described above.
- means (d) is typically a means that is capable of determining the hematocrit corrected analyte concentration using the equations described above, where this means typically comprises the hematocrit correction factor.
- An electrochemical test st ⁇ p consisting of two metallized electrodes o ⁇ ented in a sandwich configuration was prepared as follows
- the top layer of the test st ⁇ p was a gold sputtered Mylar strip
- the middle layer was a double-sided adhesive with a punched hole that defined the reaction zone or area
- the punched hole was a circle with two juxtaposed rectangular inlet and outlet channels
- the bottom layer of the test st ⁇ p was sputtered palladium on Mylar A film of fern cyanide and glucose dehydrogenase PQQ was deposited on the palladium sputtered surface
- First and second time current transients for a number of different samples varying by glucose concentration and hematocrit were obtained as follows Sample was applied to the st ⁇ p which actuated an applied potential of - 03 V for a pe ⁇ od of 10 seconds which was then followed by a second pulse of +0 3 V for a pe ⁇ od of 3 to 10 seconds (where these electrode potentials are with respect to the gold electrode)
- C o is the preliminary concentration of the analyte
- F is faraday's constant
- A is the area of the electrode surface
- variable ⁇ was derived using the equation where iss is the steady-state current of the second applied electric potential or second pulse, and ip P is the average current from 8 5 to 9 5 seconds of the 10 s long period during which the first pulse was applied
- Hematocrit Correction Factor l/((0 6637) + ((4 9466*ln(C 0 ))/ C 0 ) + (-0 4012*ln( ⁇ ))) The above correction factor was found to be valid for those situations where the ⁇ >0 7 and Co >40 mg/dL
- a prediction data set was generated by testing several glucose strips with a wide range of glucose and hematocrit levels From this data a hematocrit correction equation was derived using a model which fits the terms C 0 , ⁇ , and ⁇ (C 0 , ⁇ ) It was found that using the hematocrit correction equation on the prediction data set causes the majority of data points to fall within +/- 15% It was also found that the bias of the glucose results to 42%) hematoc ⁇ t, indicating that the hematocrit effect on this data set is minimal In order to confirm this algorithm, another batch of glucose sesnsors was tested with a different blood donor It was found that the algorithm still corrects for the hematocrit effect in a manner analogous to the earlier findings.
Abstract
Description
Claims
Priority Applications (12)
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AT01905055T ATE313794T1 (en) | 2000-02-02 | 2001-01-25 | ELECTROCHEMICAL METHODS AND DEVICES FOR USE IN MEASURING ANALYTE CONCENTRATIONS WITH CORRECTED HEMATOCRIT |
DE60116056T DE60116056T2 (en) | 2000-02-02 | 2001-01-25 | ELECTROCHEMICAL PROCESSES AND DEVICES FOR USE IN THE MEASUREMENT OF ANALYZ CONCENTRATIONS WITH CORRECTED HAEMATOCRITING VALUE |
IL14966201A IL149662A (en) | 2000-02-02 | 2001-01-25 | Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations |
JP2001556308A JP2003521708A (en) | 2000-02-02 | 2001-01-25 | Electrochemical method and apparatus used for measurement of analyte concentration with corrected hematocrit value |
EP01905055A EP1252514B1 (en) | 2000-02-02 | 2001-01-25 | Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations |
PL01358492A PL358492A1 (en) | 2000-02-02 | 2001-01-25 | Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations |
KR1020027009882A KR20020077409A (en) | 2000-02-02 | 2001-01-25 | Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations |
CA002398203A CA2398203A1 (en) | 2000-02-02 | 2001-01-25 | Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations |
AU32974/01A AU783311B2 (en) | 2000-02-02 | 2001-01-25 | Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations |
MXPA02005797A MXPA02005797A (en) | 2000-02-02 | 2001-01-25 | Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations. |
HK03101950.3A HK1049881B (en) | 2000-02-02 | 2003-03-17 | Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations |
AU2006200073A AU2006200073A1 (en) | 2000-02-02 | 2006-01-09 | Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations |
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US09/497,304 | 2000-02-02 | ||
US09/497,304 US6475372B1 (en) | 2000-02-02 | 2000-02-02 | Electrochemical methods and devices for use in the determination of hematocrit corrected analyte concentrations |
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US (3) | US6475372B1 (en) |
EP (2) | EP1252514B1 (en) |
JP (1) | JP2003521708A (en) |
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HK (1) | HK1049881B (en) |
IL (1) | IL149662A (en) |
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AU783311B2 (en) | 2005-10-13 |
HK1049881A1 (en) | 2003-05-30 |
PL358492A1 (en) | 2004-08-09 |
RU2002116217A (en) | 2004-01-20 |
AU3297401A (en) | 2001-08-14 |
DK1252514T3 (en) | 2006-05-01 |
US6475372B1 (en) | 2002-11-05 |
EP1252514A2 (en) | 2002-10-30 |
EP1645876A2 (en) | 2006-04-12 |
MXPA02005797A (en) | 2003-10-14 |
CN1394280A (en) | 2003-01-29 |
CZ20021298A3 (en) | 2003-05-14 |
EP1645876A3 (en) | 2008-03-05 |
HK1049881B (en) | 2006-09-08 |
WO2001057510A3 (en) | 2002-02-21 |
RU2005123794A (en) | 2007-02-10 |
CN1193228C (en) | 2005-03-16 |
US20050176153A1 (en) | 2005-08-11 |
US20020125145A1 (en) | 2002-09-12 |
EP1252514B1 (en) | 2005-12-21 |
TW520439B (en) | 2003-02-11 |
ES2254368T3 (en) | 2006-06-16 |
KR20020077409A (en) | 2002-10-11 |
MY127335A (en) | 2006-11-30 |
JP2003521708A (en) | 2003-07-15 |
RU2262890C2 (en) | 2005-10-27 |
IL149662A (en) | 2005-07-25 |
IL149662A0 (en) | 2002-11-10 |
ATE313794T1 (en) | 2006-01-15 |
AR027345A1 (en) | 2003-03-26 |
DE60116056D1 (en) | 2006-01-26 |
US6890421B2 (en) | 2005-05-10 |
CA2398203A1 (en) | 2001-08-09 |
DE60116056T2 (en) | 2006-08-10 |
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