WO2008034587A1 - Bestimmung von wasserstoffperoxidkonzentrationen - Google Patents
Bestimmung von wasserstoffperoxidkonzentrationen Download PDFInfo
- Publication number
- WO2008034587A1 WO2008034587A1 PCT/EP2007/008121 EP2007008121W WO2008034587A1 WO 2008034587 A1 WO2008034587 A1 WO 2008034587A1 EP 2007008121 W EP2007008121 W EP 2007008121W WO 2008034587 A1 WO2008034587 A1 WO 2008034587A1
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- WIPO (PCT)
- Prior art keywords
- measuring
- potential
- hydrogen peroxide
- concentration
- electrodes
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Classifications
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- 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
- 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
- G01N27/3273—Devices therefor, e.g. test element readers, circuitry
Definitions
- the invention relates to a method and a device for determining hydrogen peroxide concentrations in liquids, in particular an improved determination of hydrogen peroxide concentrations in blood, sweat, urine or milk.
- the determination of substances, especially in the presence of other, partly interfering substances, is important for many applications, especially in medical diagnostics.
- the determination of glucose in the blood is of crucial importance for diabetes therapy.
- the therapy is particularly promising if the blood sugar is controlled by the patient himself at regular intervals.
- the patient pricks himself with a lancing device to get a drop of blood, which he applies to a disposable biosensor.
- This is contained in a measuring device that carries out the measurement and the evaluation.
- the display shows the blood glucose value after 10 to 30 seconds, which is used by the patient for ongoing control and / or precise insulin dosing.
- optical methods reflection or absorption spectroscopy is used to detect the amount of chromophore formed in the reaction with glucose in the blood.
- the intensity of the color change is proportional to the blood sugar content.
- Electrochemical methods use amperometric or coulometric methods to determine the blood sugar content.
- the possible use and, above all, the efficiency of electrochemical methods is limited by the large number of interfering substances (urea, amino acids, ascorbic acid, medicines, etc.) in the blood, since these can also be converted at the electrodes and thus deliver incorrectly elevated values.
- the hematocrit is the proportion of red blood cells in the whole blood (in% by volume).
- the normal hematocrit is between 40 and 45% by volume. In case of illness or in accidents with high blood loss, the Hk can be between about 22 and 65% by volume.
- Electrochemical disposable sensors usually consist of a substrate on which contacts, lines and electrodes are formed from a conductive material.
- the reaction zone and the contacts to the meter are defined by applying a non-conductive layer.
- the reaction zone is formed by the electrodes.
- two electrodes are found, one serving as a measuring electrode.
- the other represents the reference and counterelectrode.
- the actual detection reaction takes place at the measuring electrode.
- an enzyme layer or membrane is applied on or in front of it.
- the enzyme is used to specifically react with the glucose in the blood.
- the measuring electrode now measures the concentration of one or more reaction products of the enzyme reaction. As long as the activity of the enzyme is higher than the substrate concentration, the concentration of the reaction products is directly proportional to the substrate concentration. The measuring electrode thus directly determines the glucose concentration in the blood.
- the determination of glucose can be based on either (1) the consumption of oxygen (O r electrodes); (2) the hydrogen peroxide formed (H 2 O 2 - electrodes) or (3) the increase in the pH (pH electrodes) take place.
- Glucose sensors based on pH changes have the disadvantage that their measurement behavior is determined by the buffer capacity of the sample.
- the measured value over a more or less large area is directly proportional to the glucose concentration.
- the measuring range is determined by the permeability of the membrane for glucose and oxygen. High permeability of the membrane provides high sensitivity, while low permeability reduces the sensitivity but extends the measurement range. At high glucose concentrations, the measuring range can be limited by insufficient enzyme activity. However, this circumstance can be contained by using excess enzyme. Care must be taken to ensure that self-inhibition occurs, especially in the case of glucoses oxidase at high enzyme levels.
- the measuring range is limited by the transport speed of oxygen to the enzyme to a maximum of 200 mg / dl.
- blood sugar levels between 200 and 500 mg / dl are the order of the day.
- oxygen-independent glucose sensors have been developed.
- mediators M Other molecules than oxygen take over the transport of the electrons from the redox center of the enzyme to the electrode surface. These molecules are called mediators M. The mechanism works according to the following scheme: Glucose + GOD 0x (( ⁇ -glucolactone + GOD red (II)
- Such sensors are to some extent oxygen independent and work even in anaerobic environments.
- mediators examples include benzo and naphthoquinones (EP 0 190 740), substituted flavins, phenazines, phenothiazines, indophenols, substituted 1,4-benzoquinones and indamines (EP 0 330 517), N-oxides, nitroso compounds, hydroxylamines and oxines (EP 0 354 441), soluble hexacyanoferrate / iron compounds (EP 0 496 730) or phenazinimium / phenoxazinium salts (US Pat. No. 3,791,988).
- glucose sensors with mediators have disadvantages. So all mediators are poisonous.
- the natural reaction of glucose oxidase with oxygen from the medium can not be prevented, since the affinity of the redox center to O 2 is about 100 times higher than eg to Fe (III) CN 6 . This is especially noticeable at low glucose concentration and leads to low readings because the H 2 O 2 formed by the reaction with oxygen is not detected.
- In the production of such sensors must like It must be ensured that the mediator remains in the oxidized state until the measurement. Each partial reduction leads to an increased background current, since M red molecules are already present, which of course are also implemented. It is known (EP 0 741 186) that especially at high temperatures and high humidity mediators tend to reduce rapidly. This naturally reduces the durability and thus the possibility of using the sensors as disposable sensors.
- the working electrodes and the counter electrodes are generally made of platinum, gold, carbon or the like.
- the reference electrode is an Ag-AgCl electrode, a calomel electrode or the same material as the working electrode.
- WO 81/03546 discloses a method for measuring the glucose concentration, in which a potential profile (lower limit: -1.0 to -0.6 V, upper limit: 0.7 to 1.1 V) with Holding times at certain points (especially where glucose is converted) and at reversal points. In certain areas, the charge is determined. Breakpoint and hold times are chosen so that the charge is proportional to the glucose concentration, independent of interfering substances, mainly urea and amino acids.
- the areas in which integration takes place are characterized by the fact that glucose always only makes a positive contribution to the total charge, while the interfering substances provide both positive and negative contributions, which are thus averaged out during integration.
- this method fails at high concentrations of interfering substances and at the same time low concentrations of glucose.
- a method for determining glucose in the blood which works with H 2 O 2 electrodes without mediators, is relatively insensitive to hematocrit and temperature at which the H 2 O 2 - detection can be carried out in a lower potential range, desirable he becomes insensitive to Störspezies.
- the sensors should be storable so that they can be used as disposable sensors.
- An object of the present invention is therefore to improve the accuracy of the amperometric determination of hydrogen peroxide concentrations in a liquid sample, in particular in blood, sweat, urine or milk, and in particular to further reduce or completely eliminate the influence of Störsubsubstanzen on the result of the determination ,
- One embodiment of the invention is a method for the amperometric determination of the in a liquid sample, in particular blood, Se plasma, urine, interstitial fluid, sweat or milk concentration of hydrogen peroxide by means of electrodes to which different potentials E are applied during a measuring cycle.
- the method comprises the measurement at a potential E M suitable for measuring the hydrogen peroxide concentration in the liquid sample and the measurement at at least one potential E K suitable for measuring the concentration of a substance in the liquid sample used in the measurement of the Hydrogen peroxide concentration acts as a disruptive substance, in particular urea, amino acids, ascorbic acid and certain drugs.
- the result / results of the additional measurement (s) at one or more potential (s) E 101 is suitable for measuring the concentration of an interfering substance in the liquid sample are / may be / may be used to study the influence of an interfering substance (s ) to the result of the measurement at the potential suitable for measuring the hydrogen peroxide concentration in the liquid sample. This makes the result of the glucose determination insensitive to the influence of one or more interfering substances contained in the fluid sample in an unknown concentration.
- a potential is applied at which the current flowing between the electrodes varies essentially linearly, but at most exponentially with the hydrogen peroxide concentration or with the interfering substance concentration.
- the results of the measurements are at the potentials suitable for measuring the concentration of interfering substances, each multiplied by a previously empirically determined weighting factor a. deducted.
- the total current at the typical hydrogen peroxide potential is corrected by means of the measuring currents at various typical interfering substance potentials multiplied by a weighting factor, and thus results in a more simple and accurate value.
- the measurements are repeated at the different potentials, typically until a certain convergence criterion is reached.
- a certain convergence criterion is reached.
- an activation potential is applied prior to application of the first measurement potential, which is typically between -200 and +700 mV, preferably at 0V.
- the measuring potential can be shifted far into the cathodic.
- a maximum of 10 different potentials are applied, and typically 4, which are in the ranges of -1200 to -800 mV, -600 to 0 mV, -200 to +700 mV, and +200 to +1400 mV.
- the measuring potentials that are applied for determining the concentrations of the interfering substances are generally more cathodic than the measuring potential E M , so that little substrate is consumed.
- the hydrogen peroxide is the end product of an enzyme reaction.
- at least one oxo reductase is preferably used, for example glucose oxidase in the case of glucose determination.
- substrates can be determined by other suitable enzymes, such as lactate oxidase, cholesterol oxidase, alkohydehydrogenase, xanthine oxidase, amino acid oxidase, ascorbic acid oxidase, acyl-CoA oxidase, uricase, glutamate dehydrogenase, fructose dehydrogenase or the like.
- suitable enzymes such as lactate oxidase, cholesterol oxidase, alkohydehydrogenase, xanthine oxidase, amino acid oxidase, ascorbic acid oxidase, acyl-CoA oxidase, uricase, glutamate dehydrogenase, fructose dehydrogenase or the like.
- gold electrodes are used as electrodes.
- measuring devices by means of which the method described above can be carried out.
- These measuring devices may have the measuring electrodes integrated, e.g. on a measuring chip, or the measuring electrodes are mounted on an external measuring strip, which is electrically connected to the measuring device.
- the electrochemical potential drops in the liquid sample are preferably compensated via a control circuit.
- the potential of the measuring electrode is kept at a constant value by a control circuit during the entire measurement.
- Fig. 1 shows a typical course of a potential applied to the measuring electrodes
- Fig. 2 shows a typical course of the measuring current in response to the potential curve shown in Fig. 1;
- Fig. 3 shows the schematic structure of a test strip suitable for carrying out the measurement
- Fig. 6 shows a control circuit for impressing the potential levels according to the invention.
- At least one potential is chosen so that it is suitable for measuring the hydrogen peroxide concentration.
- this is a potential at which the measurement current is linear or maximally exponential to the hydrogen peroxide concentration, i. varies linearly or exponentially with a change in hydrogen peroxide concentration.
- At least one potential is selected such that it is suitable for measuring the concentration of a substance which acts as a disruptive substance in the above measurement of the hydrogen peroxide concentration, that is, influences, in particular amplifies, the current flowing between the electrodes in the hydrogen peroxide measurement.
- Such an additional measuring potential thus permits the estimation of the concentration of a particular interfering substance and is in particular a potential at which the measuring current is not linear to the hydrogen peroxide concentration but to the concentration of the interfering substance.
- the estimation (s) of the interfering substance (s) can then be used as a correction factor for the preliminary estimation of the hydrogen peroxide concentration by estimating the current that the interfering substance (s) measure at the hydrogen peroxide potential measure, and the reading is corrected accordingly. If the measured value is, for example, the strength of the measuring current flowing at the potential for hydrogen peroxide measurement, then the estimated value of the contribution of the interfering substances determined by the above method to this measured value can be subtracted from this measured value.
- the actually measurable concentration is then determined according to the method described above for the interfering substances kl, kl,... Kn with a typical potential EK for the measurement of the interfering substance concentration.
- This typical potential is, for example, a potential at which the measuring current is linear with the concentration of the interfering substance.
- E M typical for the measurement of the hydrogen peroxide concentration
- the preliminary value of the hydrogen peroxide concentration is determined, whereby the current value I M is obtained as the measured value.
- the constants a ,, a 2 , ..., a are weighting factors that have to be determined empirically in preliminary experiments in the laboratory. They are necessary because hu h h ⁇ • h n , as noted above, at the potentials E k2 , ..., E kn are measured, the E k of E M being different, typically smaller.
- the relationship is no longer linear because the substances influence one another. The relationship varies depending on the concentration of interfering substances and the amount of other components that are still present. In total, ⁇ takes several factors.
- the above working formula is programmed into the meter.
- factors can be included in the calculation of the blood sugar concentration and can also supplement the above working formula.
- factors include, in particular, an estimation of the proportion of the measuring current caused by those interfering substances whose concentration is not measured separately by the above method.
- physical and physiological properties such as the temperature of the sample can influence the measurement currents.
- the measuring strip consists of three electrodes (14): measuring, counter and reference electrodes.
- the substrate 10 consists of a thermoplastic plastic film (eg PVC from Ineos, Germany).
- Electrodes 11 eg Duplo Bond ® from Lohmann, Germany
- a hydrophilic-coated cover film 12 such as Hostaphan ® RN HSTE by Mitsubishi Polyester film, Germany
- the glucose oxidase is screen-printed on the electrode surface (eg HEMA GX from Aurum Technology, Austria).
- the potential ranges are for the typical case for example:
- E A is an activation potential.
- Gold electrodes are known to undergo oxidation of H 2 O 2 at two different potentials (M. Gerlache et al., Electrochimica Acta, Vol. 43, No. 23, pages 3467 to 3473, 1998).
- the height above all of the first peak depends very much on the nature of the electrode and the composition of the medium.
- the formation of the first peak is accelerated by adsorbed OH ions on the gold surface.
- the first peak forms only weakly or not at all.
- this first peak is particularly suitable for the detection of H 2 O 2 , since the half-wave potentials of F 2 O 2 oxidation and of oxide formation are separated from one another. This allows more sensitive measuring, such as with platinum electrodes, in which the oxide formation is always mitge messenger in the H 2 O 2 detection.
- the blood glucose concentration G can then be derived directly from IM, since it is proportional to the hydrogen peroxide concentration, which in turn is proportional to Iw (in this case referred to as hz). G results with the intercept d and the slope k (both from the calibration) to:
- the potential suitable for measuring the hydrogen peroxide concentration is between +200 and +1400 mV. In the potential range between +770 and +1030 mV, the confidence interval (without correction term) is 95%.
- FIG. 1 shows an example of a curve of the voltage applied between the measuring electrodes with four potential steps P t to P 4 .
- the largest anodic potential - P 2 in Fig. 1 - is typically the potential suitable for measuring hydrogen peroxide concentration.
- the potential P 1 corresponds to the activation potential E A for the reduction of the measuring potential £ w to ⁇ 0.6 V (NHE). Accordingly P 3 and P 4 represent potential levels that are suitable for measuring two different disturbances.
- the four time periods t ⁇ measured to t 4 measured identify the periods during which measurements can be performed: f measured is the time period during which can be performed on the hydrogen peroxide concentration measurements (or multiple pulsed measurements) in relation; t 3 mess and t 4 mess are the time periods during which the measurements in relation to the interfering substances can be carried out.
- t ' mess only plays a role in iterative measurement in the first cycle. Here it serves to check whether the test strip is in order. In subsequent cycles, no measurement is made at Pi.
- the measuring periods are at the end of the period in which a potential level is applied.
- FIG. 2 clearly shows how the current between the measuring electrodes does not become stable until the end of each period in which a potential is applied. These ends correspond to the four measurement periods / mess to t meas-
- the measurement potentials and the corresponding measurements are preferably, as already mentioned above, not only run once but repeated. If so If certain blood glucose value G is no longer changed, this final value is shown on the display.
- the circuit for impressing the potential levels according to the invention is shown in FIG.
- the potential of the measuring electrode is kept at a constant value via the contact 27 through the operational amplifier (OP) 21 (pin 5, 6, 7).
- OP operational amplifier
- DAC digital-to-analogue converter
- up to ten potential levels of different height and length are generated and impressed on the controller 22 (pins 8, 9, 10) as a setpoint.
- the controller 22 compensates for electrochemical potential drops in the blood during the measurement (IR compensation).
- the potential between the measuring electrode and the reference electrode (connected to the measuring device via contact 25) therefore follows the nominal value.
- the current of the electrodes flows through the measuring resistor R, vi ess (27) and generates there a voltage drop.
- the controller 23 (pin 1, 2, 3) brings as a voltage follower the potential VSINK of the measuring electrode to the analog-to-digital converter (ADC, not shown), the controller 21 (pin 5, 6, 7), the voltage after the measuring resistor 24th (U ADC ).
- ADC analog-to-digital converter
- U ADC the voltage after the measuring resistor 24th
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Abstract
Description
Claims
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US12/441,716 US9938555B2 (en) | 2006-09-18 | 2007-09-18 | Determination of hydrogen peroxide concentrations |
CN200780034519.XA CN101583721B (zh) | 2006-09-18 | 2007-09-18 | 过氧化氢浓度的测定 |
EP07818223A EP2066801A1 (de) | 2006-09-18 | 2007-09-18 | Bestimmung von wasserstoffperoxidkonzentrationen |
CA002663664A CA2663664A1 (en) | 2006-09-18 | 2007-09-18 | Determination of hydrogen peroxide concentrations |
AU2007299248A AU2007299248A1 (en) | 2006-09-18 | 2007-09-18 | Determination of hydrogen peroxide concentrations |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE102006043718.7A DE102006043718B4 (de) | 2006-09-18 | 2006-09-18 | Bestimmung von Wasserstoffperoxidkonzentrationen |
DE102006043718.7 | 2006-09-18 |
Publications (1)
Publication Number | Publication Date |
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WO2008034587A1 true WO2008034587A1 (de) | 2008-03-27 |
Family
ID=38920780
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/EP2007/008121 WO2008034587A1 (de) | 2006-09-18 | 2007-09-18 | Bestimmung von wasserstoffperoxidkonzentrationen |
Country Status (9)
Country | Link |
---|---|
US (1) | US9938555B2 (de) |
EP (1) | EP2066801A1 (de) |
CN (1) | CN101583721B (de) |
AU (1) | AU2007299248A1 (de) |
CA (1) | CA2663664A1 (de) |
DE (1) | DE102006043718B4 (de) |
RU (1) | RU2444006C2 (de) |
WO (1) | WO2008034587A1 (de) |
ZA (1) | ZA200901881B (de) |
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RU2276354C1 (ru) * | 2005-02-17 | 2006-05-10 | Государственное образовательное учреждение высшего профессионального образования Томский политехнический университет | Способ количественного определения стрептомицина методом инверсионной вольтамперометрии |
EP1860432B1 (de) * | 2006-05-24 | 2017-12-13 | Bionime GmbH | Verfahren zum Betrieb eines Messgeräts und Messgerät |
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2006
- 2006-09-18 DE DE102006043718.7A patent/DE102006043718B4/de not_active Expired - Fee Related
-
2007
- 2007-09-18 CN CN200780034519.XA patent/CN101583721B/zh not_active Expired - Fee Related
- 2007-09-18 AU AU2007299248A patent/AU2007299248A1/en not_active Abandoned
- 2007-09-18 WO PCT/EP2007/008121 patent/WO2008034587A1/de active Application Filing
- 2007-09-18 RU RU2009114746/28A patent/RU2444006C2/ru not_active IP Right Cessation
- 2007-09-18 EP EP07818223A patent/EP2066801A1/de not_active Withdrawn
- 2007-09-18 US US12/441,716 patent/US9938555B2/en not_active Expired - Fee Related
- 2007-09-18 CA CA002663664A patent/CA2663664A1/en not_active Abandoned
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2009
- 2009-03-17 ZA ZA200901881A patent/ZA200901881B/xx unknown
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Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
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US20120199497A1 (en) * | 2011-02-07 | 2012-08-09 | Lifescan Scotland Limited | Electrochemical-based analytical test strip with diffusion-controlling layer and method for determining an analyte using such an test strip |
CN107110813A (zh) * | 2014-12-18 | 2017-08-29 | 雷迪奥米特医学公司 | 对内源性调节剂进行校正的安培型肌酸酐传感器的校准概念 |
CN107110813B (zh) * | 2014-12-18 | 2020-04-17 | 雷迪奥米特医学公司 | 对内源性调节剂进行校正的安培型肌酸酐传感器的校准概念 |
US11209382B2 (en) | 2014-12-18 | 2021-12-28 | Radiometer Medical Aps | Calibration concept for amperometric creatinine sensor correcting for endogenous modulators |
Also Published As
Publication number | Publication date |
---|---|
RU2009114746A (ru) | 2010-10-27 |
EP2066801A1 (de) | 2009-06-10 |
CN101583721A (zh) | 2009-11-18 |
DE102006043718B4 (de) | 2014-12-31 |
CN101583721B (zh) | 2015-06-24 |
AU2007299248A1 (en) | 2008-03-27 |
ZA200901881B (en) | 2010-08-25 |
DE102006043718A1 (de) | 2008-03-27 |
US9938555B2 (en) | 2018-04-10 |
RU2444006C2 (ru) | 2012-02-27 |
US20100258451A1 (en) | 2010-10-14 |
CA2663664A1 (en) | 2008-03-27 |
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