CN111812175B - Blood detection method for reducing interference of hematocrit and biosensor - Google Patents
Blood detection method for reducing interference of hematocrit and biosensor Download PDFInfo
- Publication number
- CN111812175B CN111812175B CN202010610914.5A CN202010610914A CN111812175B CN 111812175 B CN111812175 B CN 111812175B CN 202010610914 A CN202010610914 A CN 202010610914A CN 111812175 B CN111812175 B CN 111812175B
- Authority
- CN
- China
- Prior art keywords
- blood
- target analyte
- concentration
- value
- enzyme
- 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.)
- Active
Links
Images
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
- G01N27/3273—Devices therefor, e.g. test element readers, circuitry
-
- 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
- G01N27/416—Systems
- G01N27/4163—Systems checking the operation of, or calibrating, the measuring apparatus
Abstract
A blood detection method and biosensor for reducing interference of hematocrit is used for determining the concentration of a target analyte in a blood sample to be detected, and the detection method comprises the following steps: contacting a blood sample to be detected with an enzyme electrode, and carrying out chemical reaction on a target analyte in the blood sample to be detected and biological recognition enzyme; wherein the target analyte is blood glucose, uric acid or blood ketone; applying voltage to the enzyme electrode to obtain the response current of the target analyte, starting timing, and sequentially selecting five time points to obtain corresponding current values; step three, acquiring five current values I obtained in the step twot1、It2、It3、It4、It5The concentration of the target analyte is calculated by bringing the concentration into a calculation formula, and the technical problems that the prior art is not simultaneously suitable for a method for reducing the interference of hematocrit on blood sugar, uric acid and blood ketone concentration results, the prior art is complex and time-consuming, the cost is high, and new interference factors are introduced to cause inaccurate measurement results are solved.
Description
Technical Field
The invention relates to the technical field of electrochemical detection, in particular to an electrochemical blood detection method for reducing hematocrit interference and an electrochemical biosensor adopting the method.
Background
The quantitative determination of the concentration of important substances in human blood, such as blood glucose, blood ketones, blood lactate, cholesterol, uric acid, triglycerides, blood coagulation factors, anticoagulation factors, etc., is very important for diagnosis and health management. For example, for a diabetic who must measure the glucose concentration in the blood to control the glucose intake in his diet, it is very necessary to measure the glucose concentration in the blood.
Currently, electrochemical biosensors, which are generally three-electrode systems including a working electrode, a reference electrode, and an auxiliary electrode, are mainly used to measure the concentration of a target analyte in blood. Bioactive molecules are fixed on the surface of a working electrode as a recognition object, and the bioactive molecules and a target analyte are subjected to chemical reaction by applying a control voltage between the working electrode and a reference electrode to generate a trace reaction current, wherein the current intensity is changed along with the concentration of the target analyte. And converting the generated current value into the concentration of the analyte, thereby carrying out quantitative analysis on the target analyte. The sensor has the advantages of simple operation, small sample amount, high accuracy, low manufacturing cost, real-time detection and the like, and is widely applied to the field of in vitro diagnosis. However, current electrochemical biosensors are susceptible to hematocrit when testing the concentration of an analyte in a blood sample, thereby interfering with the results of testing the analyte concentration, particularly when determining blood glucose, uric acid and blood ketone concentrations. This is because the movement and diffusion rate of the oxidation/reduction substance depend on the hematocrit, and therefore, the detection current signal is greatly affected.
Hematocrit (HCT), also known as Hematocrit, is the relative proportion of the volume of red blood cells in a given volume, generally speaking, normal men are basically between 40% and 50%; the HCT of normal women is basically 37-48%. However, for patients or particular populations, HCT may be less than 35% or greater than 50%. Such as pregnancy, anemia, or therapy, the hematocrit may be reduced, even below 20% in some extreme cases; the hematocrit of the newborn is high, usually 50% -65%, and even 70% in some children with polycythemia. The HCT influences the measurement result of the blood glucose concentration, and the HCT is characterized in that when the hematocrit is lower, the test current generated by the glucose in the blood sample is larger, so that the measurement result is higher; when the hematocrit is higher, the test current generated by glucose in the blood sample is smaller, resulting in a lower measurement result.
In order to obtain more accurate blood glucose concentration measurements, the effect of hematocrit must be considered, and in order to reduce the effect of hematocrit, the prior art has been directed to reducing or avoiding HCT interference in two directions, namely, to remove the red blood cells, i.e., to avoid the red blood cells from contacting the electrodes. For example, in chinese patent CN107436318A, anti-erythrocyte antibody magnetic beads are provided on an enzyme layer, and erythrocytes are attracted to the magnetic layer by the cooperation of the magnetic layer and the anti-erythrocyte antibody magnetic beads, so that erythrocytes are not present between the electrodes. Chinese patent CN104931560A introduces erythrocyte agglutinating agent into reagent components to promote erythrocyte agglutination, so that agglutination with larger size is formed, and erythrocytes are filtered. The second is calibration, i.e. measuring the actual HCT value. For example, the chinese patent CN109884150A measures the AD value of the hematocrit of the sample, converts the AD value into the sample resistance value, and calculates the initial hematocrit value by the correlation equation. Chinese patent CN108680622A adopts the resistance values (R) of different hematocrit blood samples to make a correlation curve, and determines the hematocrit value (HCT) of the detected blood sample. Both removal of red blood cells and measurement of the actual HCT value increase technical difficulty and cost, and removal of red blood cells has the problems of incomplete removal and may also cause uncertainty in detection if substances are added, thereby affecting the blood glucose concentration measurement result. The actual HCT value is measured by increasing electrode test conductivity or impedance, applying different voltage or frequency signal detection and the like, which means certain complexity and test uncertainty are correspondingly increased, and the blood glucose concentration measurement result is influenced.
In order to reduce the influence of hematocrit on uric acid concentration, chinese patent CN109115853A uses HCT value determination to calibrate electrochemical uric acid measurement value by HCT influence curve on blood glucose concentration. This method still requires the determination of HCT values, increasing technical difficulty and cost.
There is currently no good correlation to reduce the effect of hematocrit on blood ketone concentration.
In view of the above, the subject of the present invention is how to design an electrochemical detection method and an electrochemical biosensor, which can reduce the interference of hematocrit on the results of blood glucose, uric acid and blood ketone concentrations in blood, and can quickly and accurately detect the blood glucose, uric acid or blood ketone concentrations without adding new interference factors.
Disclosure of Invention
The invention aims to provide a blood detection method and a biosensor for reducing interference of hematocrit, and aims to solve the technical problems that the prior art is not suitable for a method for reducing interference of hematocrit on blood sugar, uric acid and blood ketone concentration results, and the prior method for reducing interference of hematocrit on blood sugar or uric acid concentration results is complex and time-consuming, high in cost and inaccurate in measurement result due to the introduction of new interference factors.
In order to achieve the purpose, the technical scheme of the blood detection method for reducing the interference of the hematocrit is as follows:
a blood test method for reducing interference of hematocrit is used for determining the concentration of a target analyte in a blood sample to be tested; the detection method comprises the following steps:
contacting a blood sample to be detected with an enzyme electrode, and carrying out a chemical reaction on a target analyte in the blood sample to be detected and biological recognition enzyme of the enzyme electrode; wherein the target analyte is blood glucose, uric acid or blood ketone.
Step two, applying voltage to the enzyme electrode to obtain the response current of the target analyte, starting timing, and sequentially selecting five time points which are respectively t1、t2、t3、t4、t5The unit is second, and the current value corresponding to each time point is obtained and is It1、It2、It3、It4、It5The units are amperes.
Step three, acquiring five current values I according to the step twot1、It2、It3、It4、It5Calculating the concentration of the target analyte by the following formula:
in the formula: g is the concentration of the target analyte in mg/dL;
x1the value range of the constant coefficient is-10 to-3;
x2the constant coefficient is-2 to 20;
x3the value range of the constant coefficient is-2 to 30;
x4the value range of the constant coefficient is 90-100;
x5the value range of the constant coefficient is-10 to 50;
x6the constant coefficient is-20 to 30;
x7the constant coefficient is-10 to 20;
x8the value range of the constant coefficient is-30 to 40;
x9the value range of the constant coefficient is-10 to 10;
x10the constant coefficient is-10 to 10.
The relevant content in the above technical solution is explained as follows:
1. in the scheme, the enzyme electrode consists of biological recognition enzyme and a matrix electrode, and the biological recognition enzyme is fixed on the matrix electrode. The biological recognition enzyme is a substance recognition element and can perform enzymatic chemical reaction with a target analyte, and the substrate electrode is a signal conversion element and converts a concentration signal of the target analyte in a blood sample to be detected into a current signal. The above-mentioned detection principle and the structure of the electrochemical biosensor are all the prior art, and can be understood by those skilled in the art, so the present invention is not described in detail herein.
2. In the above scheme, the first step is to contact the blood sample to be tested with the enzyme electrode, so as to allow the target analyte in the blood sample to be tested to chemically react with the biological recognition enzyme of the enzyme electrode.
3. In the scheme, five time points are selected in sequence and the current value corresponding to each time point is obtained, and one time point is usually selected to obtain the corresponding current value in the prior art.
4. In the above scheme, the calculation formula in step three is an empirical formula obtained by the inventor through a large number of experimental studies and verifications, measuring the blood sugar, uric acid or blood ketone concentration, and performing formula fitting according to the current value database, preferably. Compared with the existing method for removing the red blood cells or correcting the red blood cells to reduce the interference of the red blood cells, the method does not need to add new operation steps or new substances, only needs to sequentially select five time points and obtain the current value corresponding to each time point, and then brings the five current values into a calculation formula, and the calculation formula can be simultaneously suitable for calculating the concentration of blood sugar, uric acid or blood ketone. The method provided by the invention is simple, saves the detection time, reduces the detection cost, does not introduce new interference factors, and can quickly and accurately measure the concentration of blood sugar, uric acid or blood ketone. And the method has strong universality and can be simultaneously suitable for reducing the interference of hematocrit on the concentration results of blood sugar, uric acid and blood ketone in blood.
5. In the scheme, after the blood sample to be detected is fully contacted with the enzyme electrode, voltage is applied between the working electrode and the reference electrode. The purpose of fully contacting the blood sample to be detected with the enzyme electrode is to ensure that sufficient reaction between the blood sample to be detected and the biological recognition enzyme is ensured, and the accuracy of detecting the concentration of blood sugar, uric acid or blood ketone is improved.
6. In the scheme, the voltage is direct current voltage, and the applied voltage range is 200-500 mV. And the direct-current voltage is applied, the structure is simple, and the operation is easy.
7. In the above scheme, the blood sample to be tested is a whole blood sample.
In order to achieve the purpose, the technical scheme of the biosensor adopted by the invention is as follows:
a biosensor for implementing the above blood detection method, which is a amperometric enzyme sensor; the biosensor comprises a biological recognition module, a signal conversion module and a calculation module;
the biological recognition module comprises a biological recognition enzyme membrane which is used for generating chemical reaction with the target analyte.
The signal conversion module comprises a working electrode and a reference electrode, wherein the surface of the working electrode is covered with the biological recognition enzyme film layer and is used for converting a chemical reaction signal into a current signal.
The calculation module comprises the calculation formula of the blood detection method and is used for calculating the blood detection value according to five current values It1、It2、It3、It4、It5The concentration of the target analyte is calculated.
The relevant content in the above technical solution is explained as follows:
1. in the above scheme, the working electrode and the reference electrode of the signal conversion module are signal conversion elements, and convert the target analyte concentration signal in the blood sample to be measured into a current signal. The biological recognition enzyme film layer covered on the surface of the working electrode is a recognition element, and the biological recognition enzyme can perform enzymatic chemical reaction with a target analyte. The above-mentioned detection principle and the structure of the electrochemical biosensor are all the prior art, and can be understood by those skilled in the art, so the present invention is not described in detail herein.
2. In the above scheme, when the target analyte is blood sugar, the biological recognition enzyme membrane is a glucose oxidase membrane or a glucose dehydrogenase membrane; when the target analyte is uric acid, the biological recognition enzyme membrane is a VC oxidase membrane; and when the target analyte is blood ketone, the biological recognition enzyme membrane is a beta-hydroxybutyrate dehydrogenase membrane.
3. In the above scheme, the calculation module is used for calculating the concentration of the target analyte and applying five current values It1、It2、It3、It4、It5And (4) carrying out a calculation formula in the blood detection method to calculate the concentration of the target analyte, thereby realizing quantitative analysis. The calculating module is stored in a storage medium, the storage medium can be pure hardware, such as a circuit board, or can be software, namely the calculating module is stored in the CPU in the form of program, and both the hardware and the software are stored in the prior artAs can be understood by those skilled in the art, the present invention is not described in detail herein.
The working principle and the advantages of the invention are as follows:
the method comprises the steps of calculating the concentration of blood sugar, uric acid or blood ketone in blood by adopting a mathematical empirical formula, contacting a blood sample to be detected with an enzyme electrode, carrying out chemical reaction on a target analyte in the blood sample to be detected and biological recognition enzyme of the enzyme electrode, applying voltage to the enzyme electrode, sequentially selecting five time points, obtaining a current value corresponding to each time point, substituting the five current values into the mathematical empirical formula, and calculating to obtain the concentration of the blood sugar, the uric acid or the blood ketone. Compared with the prior art, the method avoids the steps of red blood cell removal or red blood cell specific volume correction and the like, adopts a mathematical calculation formula for calculation, is simple, saves the detection time, reduces the detection cost, avoids introducing new interference factors, can quickly and accurately measure the concentration of blood sugar, uric acid or blood ketone, and obviously reduces the test error. And the method has strong universality and can be simultaneously suitable for reducing the interference of hematocrit on the concentration results of blood sugar, uric acid and blood ketone in blood.
Drawings
FIG. 1 is a graph of the deviation between a glucose reference value with a blood glucose concentration of less than 100mg/dL and a calculated value of glucose using the calculation formula of example 1;
FIG. 2 is a graph showing the deviation between a glucose reference value at a blood glucose concentration of 100mg/dL or more and a calculated glucose value using the calculation formula of example 1;
FIG. 3 is a graph of a linear regression analysis of calculated glucose values and reference glucose values of example 1;
FIG. 4 is a graph of the deviation between a glucose reference value with a blood glucose concentration of less than 100mg/dL and a calculated glucose value for a comparative example;
FIG. 5 is a graph of the deviation between a glucose reference value at a blood glucose concentration of greater than or equal to 100mg/dL and a calculated glucose value for a comparative example;
FIG. 6 is a graph of a linear regression analysis of calculated glucose values and reference glucose values for a comparative example;
FIG. 7 is a graph of the linear regression analysis of calculated uric acid values and uric acid reference values in example 2;
FIG. 8 is a graph of the linear regression analysis of the calculated blood ketone values and the reference blood ketone values of example 3.
Detailed Description
The invention is further described with reference to the following figures and examples:
example 1: blood detection method for reducing interference of hematocrit and biosensor
The target analyte in this example is blood glucose, the electrochemical biosensor is an amperometric glucose biosensor, and the detection system is a blood glucose strip and a blood glucose meter.
The blood glucose test paper comprises a substrate layer, an electrode layer, an insulating layer, a reagent layer and an enzyme film layer. The electrode layer comprises a working electrode and a reference electrode, the surface of the working electrode is coated with a biological recognition enzyme film, and the biological recognition enzyme film of the embodiment is a glucose oxidase film. The structure of the blood glucose test strip and the materials used for the layers are the prior art, which can be realized by those skilled in the art, and are not described in detail in this embodiment.
The blood glucose tester is internally provided with an integrated circuit board for processing current signals generated by the working electrode. The circuit board stores a calculation module, the calculation module comprises a calculation formula, and the mode and process for storing the calculation module are the prior art, which can be realized by a person skilled in the art, and are not described in detail in this embodiment.
The calculation formula is as follows:
in the formula: g is the blood glucose concentration in mg/dL; said x1The value is-7; x is the number of2The value is-1; x is the number of3The value is-2; x is the number of4The value is 90; x is the number of5The value is-9; x is the number of6The value is-18; x is the number of7The value is-6; x is the number of8The value is-25; x is the number of9The value is-9; x is the number of10The value is-7.
Blood glucose test preferred time point t1Is as follows0.1 second, t2Is 0.7 second, t3Is 1.9 seconds, t4At 3.5 seconds, t5At 4.8 seconds.
The blood sugar detection method comprises the following steps:
inserting the blood glucose test paper into a blood glucose tester, wherein the blood glucose test paper is communicated with a circuit of the blood glucose tester to form a complete loop, and starting the blood glucose tester. A blood sample to be tested is applied to the blood glucose test paper, and enters the test paper channel to reach the working electrode and the reference electrode through siphonage.
Step two, after the blood sample to be measured is fully contacted with the working electrode and the reference electrode, 350mV direct current voltage is applied, timing is started, and five time points are sequentially selected, wherein t is the time point1、t2、t3、t4、t5The unit is second, and the current value corresponding to each time point is obtained and is It1、It2、It3、It4、It5The units are amperes.
Step three, acquiring five current values I according to the step twot1、It2、It3、It4、It5And (4) calculating the concentration of the target analyte, substituting the concentration into a calculation formula, converting the concentration into the blood glucose concentration, and displaying the blood glucose concentration on a display screen of the blood glucose tester.
In order to verify the accuracy of the detection method of the embodiment, the following verification is carried out by referring to the experimental methods of GB/T19634-:
1. a blood glucose concentration reference value is determined. Firstly, a reference red blood cell specific volume value (HCT value) is obtained through the measurement of a capillary centrifuge, then a YSI (blood glucose) value of whole blood glucose concentration is measured through a YSI 2300 blood glucose analyzer, and then a glucose reference value (PYSI value) is calculated through a formula of PYSI (YSI/(1-0.24 HCT).
2. And calculating the deviation. When the blood sugar concentration is less than 100mg/dL, the deviation is absolute deviation, and the deviation is a glucose calculation value-glucose reference value; when the blood glucose concentration is greater than or equal to 100mg/dL, the deviation is a percentage deviation, and the deviation is (calculated glucose value-glucose reference value)/glucose reference value. The calculated value of glucose is the calculated value of blood glucose concentration, namely G obtained by substituting the blood glucose detection method into a calculation formula. GB/T19634-2005 stipulates that 95% of the blood glucose test results should meet the accuracy requirement, i.e. when the blood glucose concentration is less than 75mg/dL, the deviation does not exceed +/-15 mg/dL; when the blood sugar concentration is greater than or equal to 75mg/dL, the deviation is not more than +/-20%. ISO15197:2013 specifies that 95% of the deviation from the glucose reference should meet the accuracy requirement, i.e., the deviation is not more than + -15 mg/dL when the blood glucose concentration is less than 100 mg/dL; when the blood sugar concentration is greater than or equal to 100mg/dL, the deviation is not more than +/-15%. Referring to FIG. 1, a graph showing the deviation between the glucose reference value with a blood glucose concentration of less than 100mg/dL and the calculated glucose value using the calculation formula of this embodiment is shown, and it can be seen from FIG. 1 that the deviation falls completely within the range of. + -.10 mg/dL, which meets the relevant standard. Referring to FIG. 2, which is a graph showing the deviation between the glucose reference value with a blood glucose concentration of 100mg/dL or more and the calculated glucose value using the calculation formula of this embodiment, it can be seen from FIG. 2 that the deviation value falls mostly within the range of + -10%, rarely falls outside + -10%, but completely falls within + -15%, and meets the relevant standards. See table 1 for details:
TABLE 1 ratio of the deviation of the calculated blood glucose concentration from the reference glucose value in each range for different concentration ranges of example 1
As can be seen from Table 1, the calculated blood glucose concentrations of example 1 were within 90% of the reference PYSI value, i.e., the glucose reference, and within 100% of the reference PYSI value, i.e., within + -5 mg/dL, when the concentrations were less than 100 mg/dL; at concentrations greater than or equal to 100mg/dL, the deviation from the reference PYSI value, i.e., the glucose reference value, is 71% within. + -. 5%, 99% within. + -. 10%, and 100% within. + -. 15%. All conform to the regulations of GB/T19634-2005 and ISO15197: 2013.
3. Performing linear regression analysis on the calculated glucose value and the reference glucose value, referring to FIG. 3, which is a graph of linear regression analysis of the calculated glucose value and the reference glucose value, and referring to FIG. 3, showing the correlation coefficient R between the calculated glucose value and the reference glucose value2Reaches 0.995, which indicates that the invention is adoptedAccording to the detection method, the detected result is accurate.
Comparative example:
the comparison example is that the target analyte is blood sugar, the electrochemical biosensor is an amperometric glucose biosensor, the detection system is the conventional blood sugar test strip and a blood sugar tester, and the difference from the example 1 is that the calculation formula of the example 1 is not adopted, but the conventional internal calculation mode of the blood sugar tester is adopted, the blood sugar concentration value is obtained according to a current value, the accuracy of the measurement result is verified, and the method is the same as the verification method of the example 1.
Referring to FIG. 4, which is a graph showing the deviation between the glucose reference value having a blood glucose concentration of less than 100mg/dL and the calculated glucose value of the comparative example, it can be seen from FIG. 4 that the deviation value mostly falls within the range of. + -. 15mg/dL, meeting the relevant standards. Referring to FIG. 5, which is a graph showing the deviation between the glucose reference value at a blood glucose concentration of 100mg/dL or more and the calculated glucose value of the comparative example, it can be seen from FIG. 5 that when the hematocrit is less than 30% or more than 55%, some deviation values fall outside of. + -. 15%, and the deviation ratio does not meet the ISO15197:2013 specification.
TABLE 2 ratio of the calculated blood glucose concentration to the reference glucose concentration for different concentration ranges of the comparative examples within the respective ranges
As can be seen from Table 2, the accuracy of the test results of the comparative examples is much worse than that of example 1, particularly at blood glucose concentrations of 100mg/dL or more.
FIG. 6 is a graph of linear regression analysis of calculated glucose value and reference glucose value of comparative example, from FIG. 6, it can be seen that correlation coefficient R between calculated glucose value and reference glucose value of comparative example2Only 0.9199, which is a great difference from example 1.
Example 2: a blood detection method for reducing interference of hematocrit and a biosensor are provided, wherein a target analyte of the biosensor is uric acid, an electrochemical biosensor is a current type uric acid biosensor, and a detection system is uric acid test paper and a uric acid tester.
The uric acid test paper and the blood glucose test paper have similar structures, and the difference is that the biological recognition enzyme membrane of the uric acid test paper in the embodiment adopts a VC oxidase membrane.
The calculation formula adopted by the uric acid tester is consistent with that of example 1.
In the formula: g is uric acid concentration in mg/dL; said x1The value is-7; x is the number of2The value is 1; x is the number of3The value is 1; x is the number of4The value is 93; x is the number of5The value is-5; x is the number of6The value is 2; x is the number of7The value is-8; x is the number of8The value is-27; x is the number of9The value is-8; x is the number of10The value is 2.
Uric acid test preferred time point t1Is 0.1 second, t2Is 0.3 second, t3At 0.6 second, t4At 2.5 seconds, t5At 3.8 seconds.
The uric acid detection method is consistent with that of example 1, the calculated uric acid value and the reference uric acid value are subjected to linear regression analysis, the verification method is consistent with that of example 1, the figure 7 is a linear regression analysis graph of the calculated uric acid value and the reference uric acid value, and the figure 7 shows the correlation coefficient R of the calculated uric acid value and the reference uric acid value20.9642 is reached, which shows that the detection method of the invention is more accurate.
Example 3: blood detection method for reducing interference of hematocrit and biosensor
The target analyte in this embodiment is blood ketone, the electrochemical biosensor is an amperometric blood ketone biosensor, and the detection system is blood ketone test paper and a blood ketone tester.
The blood ketone test paper and the blood sugar test paper have similar structures, and the difference is that the biological recognition enzyme membrane of the blood ketone test paper in the embodiment adopts a beta-hydroxybutyrate dehydrogenase membrane.
The formula used for the blood ketone tester is the same as in example 1.
In the formula: g is the blood ketone concentration in mg/dL; said x1The value is-7; x is the number of2A value of 4; x is the number of3The value is-0.2; x is the number of4A value of 92;x5the value is-3; x is the number of6A value of 27; x is the number of7The value is-15; x is a radical of a fluorine atom8The value is-25; x is the number of9The value is-5; x is the number of10The value is-10.
Preferred time points t for the blood ketone test1Is 0.1 second, t21.0 second, t31.7 th second, t4At 3.5 seconds, t5At 4.4 seconds.
The blood ketone detection method is consistent with that of example 1, the linear regression analysis is carried out on the blood ketone calculated value and the blood ketone reference value, the verification method is consistent with that of example 1, the figure 8 is a linear regression analysis graph of the blood ketone calculated value and the blood ketone reference value, and the correlation coefficient R of the blood ketone calculated value and the blood ketone reference value can be seen from the figure 82Reaching 0.9448 shows that the detection result is more accurate by using the detection method of the invention.
The above embodiments are merely illustrative of the technical ideas and features of the present invention, and the purpose thereof is to enable those skilled in the art to understand the contents of the present invention and implement the present invention, and not to limit the protection scope of the present invention. All equivalent changes and modifications made according to the spirit of the present invention should be covered in the protection scope of the present invention.
Claims (7)
1. A blood test method for reducing interference of hematocrit is used for determining the concentration of a target analyte in a blood sample to be tested; the method is characterized in that: the detection method comprises the following steps:
contacting a blood sample to be detected with an enzyme electrode, and carrying out a chemical reaction on a target analyte in the blood sample to be detected and biological recognition enzyme of the enzyme electrode; wherein the target analyte is blood glucose, uric acid, or blood ketone;
step two, applying voltage to the enzyme electrode to obtain the response current of the target analyte, starting timing, and sequentially selecting five time points which are respectively t1、t2、t3、t4、t5The unit is second, and the current value corresponding to each time point is obtained and is It1、It2、It3、It4、It5In units of amperes；
Step three, acquiring five current values I according to the step twot1、It2、It3、It4、It5Calculating the concentration of the target analyte by the following formula:
in the formula: g is the concentration of the target analyte in mg/dL;
x1the value range of the constant coefficient is-10 to-3;
x2the constant coefficient is-2 to 20;
x3the value range of the constant coefficient is-2 to 30;
x4the value range of the constant coefficient is 90-100;
x5the value range of the constant coefficient is-10 to 50;
x6the constant coefficient is-20 to 30;
x7the constant coefficient is-10 to 20;
x8the value range of the constant coefficient is-30 to 40;
x9the value range of the constant coefficient is-10 to 10;
x10the constant coefficient is-10 to 10.
2. The blood detection method according to claim 1, characterized in that: after the blood sample to be tested is fully contacted with the enzyme electrode, voltage is applied to the enzyme electrode.
3. The blood detection method according to claim 1, characterized in that: the voltage is direct current voltage, and the applied voltage range is 200-500 mV.
4. The blood detection method according to claim 1, characterized in that: the blood sample to be detected is a whole blood sample.
5. The blood detection method according to claim 1, characterized in that: selecting a time point t within the time period of 0.05-0.5 seconds in the second step1Selecting a time point t within the 0.3-1.8 second time period2Selecting a time point t within the 0.5-2.8 second time period3Selecting a time point t within the time period of 2.5-5.9 seconds4Selecting a time point t within the time period of 3.5-7.0 seconds5。
6. A biosensor for carrying out the blood test method according to any one of claims 1 to 5, wherein the biosensor is a amperometric enzyme sensor; the method is characterized in that: the biosensor comprises a biological recognition module, a signal conversion module and a calculation module;
the biological recognition module comprises a biological recognition enzyme membrane which is used for generating chemical reaction with a target analyte;
the signal conversion module comprises a working electrode and a reference electrode, wherein the surface of the working electrode is covered with the biological recognition enzyme film layer and is used for converting a chemical reaction signal into a current signal;
the calculation module comprises the calculation formula of any one of claims 1 to 5, and is used for calculating the five current values I according to the five current values It1、It2、It3、It4、It5The concentration of the target analyte is calculated.
7. The biosensor of claim 6, wherein: when the target analyte is blood sugar, the biological recognition enzyme membrane is a glucose oxidase membrane or a glucose dehydrogenase membrane; when the target analyte is uric acid, the biological recognition enzyme membrane is a VC oxidase membrane; and when the target analyte is blood ketone, the biological recognition enzyme membrane is a beta-hydroxybutyrate dehydrogenase membrane.
Priority Applications (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010610914.5A CN111812175B (en) | 2020-06-30 | 2020-06-30 | Blood detection method for reducing interference of hematocrit and biosensor |
| DE212020000554.0U DE212020000554U1 (en) | 2020-06-30 | 2020-09-09 | Biosensor with reduced hematocrit interference |
| PCT/CN2020/114252 WO2022000775A1 (en) | 2020-06-30 | 2020-09-09 | Blood detection method for reducing hematocrit interference, and biosensor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010610914.5A CN111812175B (en) | 2020-06-30 | 2020-06-30 | Blood detection method for reducing interference of hematocrit and biosensor |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN111812175A CN111812175A (en) | 2020-10-23 |
| CN111812175B true CN111812175B (en) | 2022-06-14 |
Family
ID=72856310
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202010610914.5A Active CN111812175B (en) | 2020-06-30 | 2020-06-30 | Blood detection method for reducing interference of hematocrit and biosensor |
Country Status (3)
| Country | Link |
|---|---|
| CN (1) | CN111812175B (en) |
| DE (1) | DE212020000554U1 (en) |
| WO (1) | WO2022000775A1 (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN114660149A (en) * | 2022-02-23 | 2022-06-24 | 爱奥乐医疗器械(深圳)有限公司 | Electrochemical test paper and detection method |
| CN115901885B (en) * | 2023-02-15 | 2023-05-12 | 可孚医疗科技股份有限公司 | Metabolic index detection method, system and electrochemical measurement system |
Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1394280A (en) * | 2000-02-02 | 2003-01-29 | 生命扫描有限公司 | Electrochemical methods and device for use in determination of hematocrit corrected analyte concentrations |
| EP2473847A1 (en) * | 2009-09-04 | 2012-07-11 | Lifescan Scotland Limited | Glucose measurement method and system |
| CN103096793A (en) * | 2010-09-13 | 2013-05-08 | 生命扫描苏格兰有限公司 | Analyte measurement method and system with hematocrit compensation |
| CN103487475A (en) * | 2012-06-13 | 2014-01-01 | 达尔生技股份有限公司 | Calibration method, test strip and calibration system for blood glucose of blood sample |
| CN105738430A (en) * | 2014-09-17 | 2016-07-06 | 爱-森新株式会社 | Apparatus and method for measuring concentration of an analyte in whole blood samples |
| CN108680622A (en) * | 2018-05-23 | 2018-10-19 | 北京乐普医疗科技有限责任公司 | Packed cell volume measures and the method for correction in a kind of electrochemica biological sensor |
| CN111239227A (en) * | 2020-02-24 | 2020-06-05 | 江苏鱼跃医疗设备股份有限公司 | Erythrocyte volume correction method and biosensor testing device |
Family Cites Families (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5352351A (en) * | 1993-06-08 | 1994-10-04 | Boehringer Mannheim Corporation | Biosensing meter with fail/safe procedures to prevent erroneous indications |
| BRPI0510779A (en) * | 2004-05-14 | 2007-11-20 | Bayer Healthcare Llc | methods for performing hematocrit adjustment in assays and devices for same |
| CN103003692B (en) * | 2010-03-22 | 2015-01-14 | 拜尔健康护理有限责任公司 | Residual compensation for a biosensor |
| US8840776B2 (en) * | 2011-10-25 | 2014-09-23 | Bionime Corporation | Method and sensor strip for analysis of a sample |
| US9005426B2 (en) * | 2012-09-28 | 2015-04-14 | Cilag Gmbh International | System and method for determining hematocrit insensitive glucose concentration |
| EP2972271B1 (en) * | 2013-03-15 | 2018-04-18 | Roche Diabetes Care GmbH | Descriptor-based methods of electrochemically measuring an analyte |
| CN104931560A (en) | 2015-07-17 | 2015-09-23 | 王天星 | Biosensor and preparation method and application thereof |
| KR101740034B1 (en) * | 2015-07-20 | 2017-06-08 | 주식회사 아이센스 | Reagent composition of Redox reaction for detecting beta-hydroxybutyrate and electrochemical biosensor including the reagent composition |
| US20180306744A1 (en) * | 2017-04-20 | 2018-10-25 | Lifescan Scotland Limited | Analyte measurement system and method |
| CN107436318A (en) | 2017-08-17 | 2017-12-05 | 武汉璟泓万方堂医药科技股份有限公司 | A kind of electrochemistry blood testing and device for reducing red blood cell interference |
| CN109115853A (en) | 2018-09-26 | 2019-01-01 | 贵州拉雅科技有限公司 | A kind of high-precision uric acid electrochemistry test paper with hematocrit compensation |
| CN109884150B (en) | 2019-03-08 | 2021-05-14 | 武汉璟泓科技股份有限公司 | Erythrocyte backlog correction method and storage medium |
-
2020
- 2020-06-30 CN CN202010610914.5A patent/CN111812175B/en active Active
- 2020-09-09 WO PCT/CN2020/114252 patent/WO2022000775A1/en active Application Filing
- 2020-09-09 DE DE212020000554.0U patent/DE212020000554U1/en active Active
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1394280A (en) * | 2000-02-02 | 2003-01-29 | 生命扫描有限公司 | Electrochemical methods and device for use in determination of hematocrit corrected analyte concentrations |
| EP2473847A1 (en) * | 2009-09-04 | 2012-07-11 | Lifescan Scotland Limited | Glucose measurement method and system |
| CN103096793A (en) * | 2010-09-13 | 2013-05-08 | 生命扫描苏格兰有限公司 | Analyte measurement method and system with hematocrit compensation |
| CN103487475A (en) * | 2012-06-13 | 2014-01-01 | 达尔生技股份有限公司 | Calibration method, test strip and calibration system for blood glucose of blood sample |
| CN105738430A (en) * | 2014-09-17 | 2016-07-06 | 爱-森新株式会社 | Apparatus and method for measuring concentration of an analyte in whole blood samples |
| CN108680622A (en) * | 2018-05-23 | 2018-10-19 | 北京乐普医疗科技有限责任公司 | Packed cell volume measures and the method for correction in a kind of electrochemica biological sensor |
| CN111239227A (en) * | 2020-02-24 | 2020-06-05 | 江苏鱼跃医疗设备股份有限公司 | Erythrocyte volume correction method and biosensor testing device |
Also Published As
| Publication number | Publication date |
|---|---|
| DE212020000554U1 (en) | 2022-01-20 |
| WO2022000775A1 (en) | 2022-01-06 |
| CN111812175A (en) | 2020-10-23 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| EP2193367B1 (en) | Method for correcting erroneous results of measurement in biosensors and apparatus using the same | |
| JP6522067B2 (en) | System, apparatus and method for improving biosensor accuracy using fill time | |
| CN111239227B (en) | Erythrocyte volume correction method and biosensor testing device | |
| JP4988059B2 (en) | Method and apparatus for rapid electrochemical analysis | |
| AU2008221593B2 (en) | Systems and methods of discriminating control solution from a physiological sample | |
| RU2647473C2 (en) | Systems and methods for improved stability of electrochemical sensors | |
| US9335291B2 (en) | Fill sufficiency method and system | |
| TWI525322B (en) | Method of measurement of sample to be analyzed | |
| JP2003185615A (en) | Determination of sample volume adequacy | |
| WO2008049075A2 (en) | Electrochemical determination of analytes | |
| JP2001527215A (en) | Apparatus and method for determining the concentration of a medically significant component of a biological fluid | |
| CN111812175B (en) | Blood detection method for reducing interference of hematocrit and biosensor | |
| JP5139538B2 (en) | Potential difference sensor chip, potential difference measuring method, and measurement kit | |
| KR101357134B1 (en) | Method for Measuring Analytes in Blood Samples Using Electrochemical Biosensor and a Portable Analyzer | |
| CN113049652B (en) | Electrochemical measurement method | |
| WO2021169242A1 (en) | Dual-channel electrochemical biosensor and method for measuring heme concentration | |
| CN112229884A (en) | Vitamin detection printed electrode based on carbon paste modification process and preparation process thereof | |
| WO2017021534A1 (en) | System and method for compensating sample measurements using test strips | |
| CN108132284B (en) | A kind of test method of electrochemical sensor | |
| US20180231490A1 (en) | Method for calculating hematocrit in blood, method for calibrating biochemical index value in blood, and system thereof | |
| CN115876864B (en) | Test correction method and system for electrochemical biosensor | |
| US10746687B2 (en) | Method for measuring target component and apparatus for measuring target component | |
| CN111624246A (en) | Detection formula of uric acid biosensor |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| TA01 | Transfer of patent application right | ||
| TA01 | Transfer of patent application right |
Effective date of registration: 20220118 Address after: 212300 Yunyang Industrial Park, Danyang City, Zhenjiang City, Jiangsu Province Applicant after: JIANGSU YUYUE MEDICAL EQUIPMENT&SUPPLY Co.,Ltd. Applicant after: Jiangsu Yuyue kailite Biotechnology Co., Ltd Address before: 212300 Yunyang Industrial Park, Danyang City, Zhenjiang City, Jiangsu Province Applicant before: JIANGSU YUYUE MEDICAL EQUIPMENT&SUPPLY Co.,Ltd. Applicant before: JIANGSU YUYUE INFORMATION TECHNOLOGY SYSTEM Co.,Ltd. Applicant before: SUZHOU YUYUE MEDICAL TECHNOLOGY Co.,Ltd. Applicant before: SUZHOU MEDICAL APPLIANCE FACTORY Applicant before: NANJING YUWELL SOFTWARE TECHNOLOGY Co.,Ltd. |
|
| GR01 | Patent grant | ||
| GR01 | Patent grant |