Blood glucose measurement method based on hematocrit compensation, and blood glucose meter
By obtaining the impedance and current values of the blood glucose meter, determining the calibration current and hematocrit values, and using the blood glucose testing equation for compensation, the measurement error problem caused by the difference in hematocrit was solved, and accurate measurement of the electrochemical test strip was achieved.
Patent Information
- Authority / Receiving Office
- WO · WO
- Patent Type
- Applications
- Current Assignee / Owner
- GUANGDONG TRANSTEK MEDICAL ELECTRONICS CO LTD
- Filing Date
- 2025-03-19
- Publication Date
- 2026-05-15
AI Technical Summary
Differences in hematocrit among different populations lead to large errors in electrochemical blood glucose measurement results, exceeding the allowable range of national standards and affecting measurement accuracy.
By obtaining the impedance and current values detected by the blood glucose meter, the calibration current and hematocrit values are determined, and compensation is performed using the blood glucose testing equation to reduce the impact of hematocrit on the measurement results.
The measurement accuracy of the electrochemical test strip has been improved, meeting the accuracy requirements of national standards, and the influence of hematocrit on the measurement results has been reduced.
Smart Images
Figure CN2025083520_15052026_PF_FP_ABST
Abstract
Description
A blood glucose measurement method and blood glucose meter based on hematocrit compensation
[0001] Cross-reference to related applications
[0002] This application claims priority to Chinese Patent Application No. 2024116027027, filed on November 11, 2024, entitled "A Blood Glucose Measurement Method and Blood Glucose Meter Based on Hematocrit Compensation", the entire contents of which are incorporated herein by reference. Technical Field
[0003] This application relates to the field of biosensor technology, and more specifically, to a blood glucose measurement method and blood glucose meter based on hematocrit compensation. Background Technology
[0004] Electrochemical biosensors are widely used in point-of-care testing (POCT) for rapid diagnosis. These biosensors use an insulating substrate (PET substrate) as a carrier, onto which biosensor electrodes are printed. An auxiliary enzyme solution is then added to the reaction area of the substrate. The electrochemical redox reaction between the enzyme and the target analyte generates an electric current, which is used to detect the analyte by measuring the current strength. Such sensors are widely used in the auxiliary diagnosis and treatment of diabetes, such as blood glucose test strips and blood ketone test strips, and also in the diagnosis and treatment of gout and ketosis, such as uric acid test strips.
[0005] In particular, blood glucose test strips use whole blood as the test sample. The hematocrit (HCT) varies among different individuals, and the main source of error in blood glucose testing is the HCT of the sample. Hematocrit (HCT) refers to the percentage of red blood cells in the whole blood volume. When blood comes into contact with the reaction area of the electrode, if the blood sample contains more red blood cells, the effective contact area between the plasma and the electrode reaction area will decrease, resulting in a reduced electrochemical signal; conversely, if the blood sample contains fewer red blood cells, the effective contact area between the plasma and the electrode reaction area will increase, resulting in a increased electrochemical signal.
[0006] Hematocrit varies from person to person. The normal hematocrit ranges from 42% to 49% for men and 37% to 43% for women, while it ranges from 48% to 68% for newborns. However, some special patients, such as those with organ failure, anemia, or blood loss, have different hematocrits than normal individuals. Taking blood glucose as an example, the national standard GB / T 19634-2021, "General Technical Conditions for Self-Testing Blood Glucose Monitoring Systems for In Vitro Diagnostic Testing Systems," requires the following accuracy: for blood glucose concentrations < 5.55 mmol / L, the allowable deviation is ±0.83 mmol / L; for blood glucose concentrations ≥ 5.55 mmol / L, the allowable deviation is within ±15%. The hematocrit ranges from 20% to 70% in different populations. Testing within such a wide range can lead to significant deviations in blood glucose results measured by electrochemical test strips, with deviations reaching as high as 40% to 50%, far exceeding the requirement of ±15% in the national standard GB19634 / 2021.
[0007] Application content
[0008] In view of this, the purpose of this application is to provide a blood glucose measurement method and blood glucose meter based on hematocrit compensation, which compensates for the hematocrit of red blood cells in the blood through a blood glucose testing equation, reduces the influence of hematocrit on the measurement results, and thus improves the measurement accuracy of electrochemical test strips.
[0009] In a first aspect, embodiments of this application provide a blood glucose measurement method based on hematocrit compensation, applied in a blood glucose meter, wherein the method includes: acquiring the impedance value and current value of the blood sample to be tested detected by the blood glucose meter; determining a calibration current value and a hematocrit value based on the current value and impedance value, respectively; and determining the blood glucose value of the blood sample to be tested based on the hematocrit value, the calibration current value, and the blood glucose test equation.
[0010] Optionally, the calibration current value is determined by the following steps: determining the calibration current value based on the current value and a pre-set current calibration equation.
[0011] Optionally, the current calibration equation is determined by the following steps: obtaining multiple blood samples at multiple different blood glucose concentrations under multiple different hematocrit values; measuring multiple sample current values and multiple sample detection values of the multiple blood samples; and determining the current calibration equation based on the multiple sample current values and multiple sample detection values of the multiple blood samples.
[0012] Optionally, the blood glucose testing equation is determined by the following steps: obtaining multiple blood samples at multiple different blood glucose concentrations under multiple different hematocrit values and the actual hematocrit values of the multiple blood samples; fitting the multiple blood samples at multiple different blood glucose concentrations under multiple different hematocrit values and the actual hematocrit values of the multiple blood samples to determine the blood glucose testing equation, wherein the blood glucose testing equation includes a first coefficient and a second coefficient, the first coefficient being determined according to a first correction equation, and the second coefficient being determined according to a second correction equation.
[0013] Optionally, the first correction equation is determined by the following steps: obtaining multiple blood samples with multiple different blood glucose concentrations and multiple different hematocrit values, as well as the actual hematocrit values of the multiple blood samples; fitting the hematocrit values, blood glucose values and actual hematocrit values of the multiple blood samples to determine the first correction equation.
[0014] Optionally, the second correction equation is determined by the following steps: obtaining multiple blood samples at multiple different blood glucose concentrations under multiple different hematocrit values and the actual hematocrit values of the multiple blood samples; fitting the hematocrit values of the multiple blood samples, the blood glucose values of the multiple blood samples and the actual hematocrit values of the multiple blood samples to determine the second correction equation.
[0015] Optionally, the blood glucose test equation is: y = Cx + D; where y is the blood glucose value of the blood to be tested, C is the first coefficient, D is the second coefficient, and x is the calibration current value.
[0016] Alternatively, the first coefficient can be determined by the following equation: C = A1H 2 +B1H+C1; where C is the first coefficient, H is the hematocrit value of the blood being tested, A1 is the first sub-coefficient, B1 is the second sub-coefficient, and C1 is the third sub-coefficient.
[0017] Alternatively, the second coefficient can be determined by the following equation: D = A²H 2 +B2H+C2; where D is the second coefficient, H is the hematocrit value of the blood being tested, A2 is the fourth sub-coefficient, B2 is the fifth sub-coefficient, and C2 is the sixth sub-coefficient.
[0018] Secondly, embodiments of this application also provide a blood glucose meter, which includes a processor, a memory, and a bus. The memory stores machine-readable instructions executable by the processor. When the electronic device is running, the processor communicates with the memory via the bus, and the processor executes the machine-readable instructions to perform the steps of any of the above methods.
[0019] The blood glucose measurement method and blood glucose meter based on hematocrit compensation provided in this application compensate for the hematocrit of red blood cells in the blood through a blood glucose testing equation, thereby reducing the influence of hematocrit on the measurement results and improving the measurement accuracy of the electrochemical test strip.
[0020] To make the above-mentioned objectives, features and advantages of this application more apparent and understandable, preferred embodiments are described below in detail with reference to the accompanying drawings. Attached Figure Description
[0021] To more clearly illustrate the technical solutions of the embodiments of this application, the accompanying drawings used in the embodiments will be briefly introduced below. It should be understood that the following drawings only show some embodiments of this application and should not be regarded as a limitation of the scope. For those skilled in the art, other related drawings can be obtained based on these drawings without creative effort.
[0022] Figure 1 is a schematic diagram of the blood glucose meter provided in the embodiment of this application;
[0023] Figure 2 is a flowchart of a blood glucose measurement based on hematocrit compensation provided in an embodiment of this application;
[0024] Figure 3 is a schematic diagram of the communication connection between the processor and the memory provided in an embodiment of this application. Detailed Implementation
[0025] To make the objectives, technical solutions, and advantages of the embodiments of this application clearer, the technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, and not all embodiments. The components of the embodiments of this application described and shown in the accompanying drawings can generally be arranged and designed in various different configurations. Therefore, the following detailed description of the embodiments of this application provided in the accompanying drawings is not intended to limit the scope of the claimed application, but merely represents selected embodiments of this application. Based on the embodiments of this application, every other embodiment obtained by those skilled in the art without inventive effort falls within the scope of protection of this application.
[0026] First, the applicable scenarios for this application will be introduced. This application can be applied to the field of biosensing technology.
[0027] Research has shown that electrochemical biosensors are widely used in point-of-care testing (POCT) for rapid diagnosis. These biosensors use an insulating substrate (PET substrate) as a carrier, printing biosensor electrodes onto it. An auxiliary enzyme solution is then added to the reaction area of the substrate. The electrochemical redox reaction between the enzyme and the target analyte generates an electric current, which is used to detect the analyte by measuring the current strength. Such sensors are widely used in the auxiliary diagnosis and treatment of diabetes, such as in blood glucose test strips and blood ketone test strips. They are also used in the diagnosis and treatment of gout and ketosis, such as in uric acid test strips.
[0028] In particular, blood glucose test strips use whole blood as the test sample. The hematocrit (HCT) varies among different individuals, and the main source of error in blood glucose testing is the HCT of the sample. Hematocrit (HCT) refers to the percentage of red blood cells in the whole blood volume. When blood comes into contact with the reaction area of the electrode, if the blood sample contains more red blood cells, the effective contact area between the plasma and the electrode reaction area will decrease, resulting in a reduced electrochemical signal (e.g., current signal, impedance signal, etc.). Conversely, if the blood sample contains fewer red blood cells, the effective contact area between the plasma and the electrode reaction area will increase, resulting in a increased electrochemical signal.
[0029] Hematocrit varies from person to person. The normal hematocrit ranges from 42% to 49% for men and 37% to 43% for women, while it ranges from 48% to 68% for newborns. However, hematocrits differ from normal individuals in certain patients, such as those with organ failure, anemia, or blood loss. Taking blood glucose as an example, the national standard GB-T 19634-2021, "General Technical Conditions for Self-Testing Blood Glucose Monitoring Systems for In Vitro Diagnostic Testing Systems," requires accuracy as follows: for blood glucose concentrations < 5.55 mmol / L, the allowable deviation is ±0.83 mmol / L; for blood glucose concentrations ≥ 5.55 mmol / L, the allowable deviation is within ±15%. Since the hematocrit range for different populations is 20%-70%, testing within such a wide range can lead to significant deviations in blood glucose results measured by electrochemical test strips, exceeding the reference value by 40%-50%. This severely affects the accuracy of blood glucose test results and may even cause the error of the blood glucose meter to significantly exceed the nationally stipulated allowable deviation range.
[0030] Based on this, the present application provides a blood glucose measurement method and blood glucose meter based on hematocrit compensation. The method compensates for the hematocrit of red blood cells in the blood through a blood glucose testing equation, thereby reducing the influence of hematocrit on the measurement results and improving the measurement accuracy of the electrochemical test strip.
[0031] Please refer to Figure 2, which is a flowchart of a blood glucose measurement method based on hematocrit compensation provided in an embodiment of this application. As shown in Figure 2, the blood glucose measurement method based on hematocrit compensation provided in this embodiment of the application includes:
[0032] S101. Obtain the impedance value and current value of the blood sample detected by the blood glucose meter.
[0033] As an example, please refer to Figure 1, which is a schematic diagram of a blood glucose meter provided in an embodiment of this application. As shown in Figure 1, the blood glucose meter provided in an embodiment of this application includes: a measuring working electrode 3, a sample measuring counter electrode 4, an impedance measuring working electrode 2, an impedance measuring counter electrode 5, a PET substrate 1, an insulating layer 6, an enzyme layer 7, a siphon channel 8, and a logo film strip 9.
[0034] Among them, the impedance measuring working electrode 2 and the impedance measuring counter electrode 5 constitute the impedance measuring electrode, and the measuring working electrode 3 and the sample measuring counter electrode 4 constitute the measuring working electrode.
[0035] Specifically, during the measurement, electrochemical parameters such as the sample detection electrode and impedance detection electrode can be measured by applying voltage or current.
[0036] The specific steps for a blood glucose meter to test current and impedance include: applying different AC frequencies and voltages in different directions; generating AC impedance and current values on the electrochemical test strip; and the instrument collecting the AC impedance signal generated on the test strip to calculate the hematocrit value of the sample.
[0037] S102. Determine the calibration current value and hematocrit value based on the current value and impedance value.
[0038] The calibration current value can be determined by the following steps: based on the current value and the current calibration equation, the calibration current value is determined.
[0039] Specifically, the current calibration equation can be determined through the following steps: obtaining multiple blood samples at multiple different blood glucose concentrations under multiple different hematocrit values; measuring multiple sample current values and multiple sample detection values of the multiple blood samples; and determining the current calibration equation based on the multiple sample current values and multiple sample detection values of the multiple blood samples.
[0040] As an example, blood samples with different hematocrit values can be configured, such as 20%, 30%, 45%, 50%, 60%, and 70%. Under each hematocrit value, blood sample samples with blood glucose concentrations of 2.8 mmol / L, 6.1 mmol / L, 15.3 mmol / L, and 29.2 mmol / L can be configured respectively.
[0041] As an example, the raw current value of a sample can be obtained by applying voltages in different ways.
[0042] There are several options for applying the voltage, such as applying a forward voltage first, followed by a reverse voltage. The optimal choice is to first apply a fixed reverse voltage, wait a certain period, then apply a forward voltage, and finally apply the reverse voltage. The voltage application time can be 2 seconds, 1 second, and 2 seconds, respectively. By applying forward and reverse voltages, the current under different hematocrit levels can be collected more accurately.
[0043] As an example, there are several options for current calibration methods, including linear fitting and multinomial fitting. Optionally, current calibration may choose linear equation fitting, i.e., I... 校准 =aI 原始 +b, where I 校准 Indicates the calibrated current, I 原始 This represents the collected current value, and a and b are the correlation coefficients.
[0044] As an example, this application provides various current data under experimental conditions. Table 1 below shows the average value of the original current test for different hematocrit and blood glucose values, and Table 2 below shows the average value of the calibrated current test for different hematocrit and blood glucose values.
[0045] Table 1:
[0046] Table 2:
[0047] As an example, by fitting the data in Tables 1 and 2, the calibration equation can be determined as follows:
[0048] I 校准 =2.34I 原始 +0.97.
[0049] Among these, the hematocrit value can be determined based on the impedance value.
[0050] Specifically, the steps for determining the hematocrit value based on the impedance value are well known to those skilled in the art and will not be described in detail here.
[0051] S103. Determine the blood glucose value of the blood to be tested based on the hematocrit value, the calibration current value, and the blood glucose test equation.
[0052] The blood glucose testing equation can be determined by the following steps: obtaining multiple blood samples at multiple blood glucose concentrations with multiple different hematocrit values and the actual hematocrit values of the multiple blood samples; fitting the multiple blood samples at multiple blood glucose concentrations with multiple different hematocrit values and the actual hematocrit values of the multiple blood samples to determine the blood glucose testing equation.
[0053] The blood glucose test equation includes a first coefficient and a second coefficient. The first coefficient is determined according to a first correction equation, and the second coefficient is determined according to a second correction equation.
[0054] As an example, taking the experimental determination of the blood glucose testing equation as an example, with the current value collected at different blood glucose concentrations on the x-axis and different blood glucose values on the y-axis, a linear equation in one variable is fitted to obtain the linear equation for blood glucose under different hematocrits. Table 3 below shows the linear equation in one variable and its fitting coefficients under different conditions.
[0055] Table 3:
[0056] Specifically, the steps for fitting multiple blood samples at multiple different blood glucose concentrations under multiple different hematocrit values and the actual hematocrit values of multiple blood samples include: determining multiple fitting equations based on the hematocrit values, blood glucose values, and blood glucose values of multiple blood samples; calculating the fitting coefficients of the multiple fitting equations; and determining that the fitting of the blood glucose test equations is complete if the fitting coefficients of the multiple fitting equations are all greater than the preset fitting correlation coefficient.
[0057] Specifically, the blood glucose test equation is: y = Cx + D;
[0058] Where y is the blood glucose value of the blood to be tested, C is the first coefficient, D is the second coefficient, and x is the calibration current value.
[0059] Specifically, the first correction equation can be determined through the following steps: obtaining multiple blood samples with different blood glucose concentrations and different hematocrit values, as well as the actual hematocrit values of the multiple blood samples; fitting the hematocrit values, blood glucose values, and actual hematocrit values of the multiple blood samples to determine the first correction equation.
[0060] In this method, the hematocrit value is used as the x-axis and the coefficient of the linear term in the corresponding equation is used as the y-axis for multivariate fitting. You can choose to perform linear fitting of the linear equation or fitting of the quadratic equation.
[0061] As an example, the first coefficient can be determined by the following equation: C = A1H2 +B1H+C1;
[0062] Wherein, C is the first coefficient, H is the hematocrit value of the blood being tested, A1 is the first sub-coefficient, B1 is the second sub-coefficient, and C1 is the third sub-coefficient.
[0063] Specifically, the second correction equation can be determined through the following steps: obtaining multiple blood samples with different blood glucose concentrations and different hematocrit values, as well as the actual hematocrit values of the multiple blood samples; fitting the hematocrit values, blood glucose values, and actual hematocrit values of the multiple blood samples to determine the second correction equation.
[0064] Specifically, the hematocrit value can be used as the x-axis and the constant term in the corresponding equation as the y-axis for multivariate fitting. You can choose linear fitting of a linear equation or fitting of a quadratic equation.
[0065] Specifically, the second coefficient can be determined using the following equation: D = A²H 2 +B2H+C2;
[0066] Where D is the second coefficient, H is the hematocrit value of the blood sample, A2 is the fourth sub-coefficient, B2 is the fifth sub-coefficient, and C2 is the sixth sub-coefficient.
[0067] For example, by fitting the data from the above multiple blood samples, we can obtain C = 6.8271H. 2 -1.4251H + 1.6547, the fitting coefficient R² of the first calibration equation for the above coefficients is calculated to be 0.9921; after fitting the data from the above multiple blood samples, D = -9.4241H can be obtained. 2 +3.3243H-2.5523, the fitting coefficient R2 of the first calibration equation with the above coefficients is calculated to be 0.8908.
[0068] As can be seen from the above example, when C = 6.8271H 2 -1.4251H + 1.6547 and D = -9.4241H 2 When +3.3243H-2.5523, the blood glucose test equation can be obtained as: y=(6.8271H 2 -1.4251H+1.6547)x+(-9.4241H 2 +3.3243H-2.5523).
[0069] Based on the above blood glucose test equation, the blood glucose measurement results in Table 4 below can be calculated.
[0070] Table 4:
[0071] Optionally, the deviation of blood glucose measurement results with different hematocrit values can be tested. By substituting the current values in Table 1, the deviation between the measured value and the reference value can be obtained. The national standard GB-T 19634-2021, "General Technical Conditions for Self-Test Blood Glucose Monitoring Systems for In Vitro Diagnostic Testing Systems," requires that when the blood glucose concentration is <5.55 mmol / L, the deviation between the measured result and the reference value should not exceed ±0.83 mmol / L; and when the concentration is ≥5.55 mmol / L, the deviation should not exceed ±15%. Based on the measurement results in Table 5, it can be seen that the accuracy meets the national standard requirements, indicating that the hematocrit compensation method of this test strip can effectively reduce the influence of hematocrit on the measurement results.
[0072] Table 5:
[0073] Specifically, to better evaluate the hematocrit correction effect of the electrochemical test strip in this application, extreme hematocrit values were selected for testing. Samples with hematocrit values of 20% and 70% were selected, and blood glucose concentrations of 3 mmol / L, 10 mmol / L, 15 mmol / L, 20 mmol / L, and 25 mmol / L were prepared, respectively. Each sample was tested 10 times, and the average value was calculated to determine the deviation from the reference value. As shown in Table 6 below, without hematocrit compensation, both the average test result and the reference value exceeded the acceptable accuracy range specified in the national standard GB-T 19634-2021 "General Technical Conditions for Self-Test Blood Glucose Monitoring Systems for In Vitro Diagnostic Testing Systems".
[0074] As an example, as shown in Table 7 below, when the hematocrit of blood samples is compensated, the average value of the test results and the reference value both meet the accuracy acceptance range in the national standard "GB / T 19634-2021 General Technical Conditions for Blood Glucose Monitoring Systems for Self-Testing in In Vitro Diagnostic Testing Systems".
[0075] Table 6:
[0076] As an example, Table 7 below shows a comparison of the deviations between the test results and the reference values when hematocrit compensation is provided.
[0077] Table 7:
[0078] The blood glucose measurement method and blood glucose meter based on hematocrit compensation provided in this application compensate for the hematocrit of red blood cells in the blood through a blood glucose testing equation, thereby reducing the influence of hematocrit on the measurement results and improving the measurement accuracy of the electrochemical test strip.
[0079] In the several embodiments provided in this application, it should be understood that the disclosed systems, apparatuses, and methods can be implemented in other ways. The apparatus embodiments described above are merely illustrative. For example, the division of units is only a logical functional division, and in actual implementation, there may be other division methods. Furthermore, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed. Additionally, the shown or discussed mutual couplings, direct couplings, or communication connections may be through some communication interfaces; indirect couplings or communication connections between devices or units may be electrical, mechanical, or other forms.
[0080] The units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple network units. Some or all of the units can be selected to achieve the purpose of this embodiment according to actual needs.
[0081] In addition, the functional units in the various embodiments of this application can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit.
[0082] Referring to Figure 3, if the aforementioned function is implemented as a software functional unit and sold or used as an independent product, it can be stored in a non-volatile computer-readable storage medium executable by the processor 10. Based on this understanding, the technical solution of this application, in essence, or the part that contributes to the prior art, or a part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions to cause a computer device (which may be a personal computer, server, or network device, etc.) to execute all or part of the steps of the methods described in the various embodiments of this application. The aforementioned storage medium includes various media capable of storing program code, such as USB flash drives, portable hard drives, read-only memory (ROM), random access memory (RAM), magnetic disks, or optical disks.
[0083] Finally, it should be noted that the above-described embodiments are merely specific implementations of this application, used to illustrate the technical solutions of this application, and not to limit them. The scope of protection of this application is not limited thereto. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that any person skilled in the art can still modify or easily conceive of changes to the technical solutions described in the foregoing embodiments, or make equivalent substitutions for some of the technical features, within the scope of the technology disclosed in this application. Such modifications, changes, or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this application, and should all be covered within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the scope of the claims.
Claims
1. A method for measuring blood glucose based on hematocrit compensation, characterized in that, Used in blood glucose meters, The method includes: Obtain the impedance and current values of the blood sample detected by the blood glucose meter; Based on the current and impedance values, determine the calibration current and hematocrit values; The blood glucose value of the blood sample to be tested is determined based on the hematocrit value, the calibration current value, and the blood glucose test equation.
2. The method according to claim 1, characterized in that, Determine the calibration current value using the following steps: The calibration current value is determined based on the current value and the pre-set current calibration equation.
3. The method according to claim 2, characterized in that, The current calibration equation is determined through the following steps: Obtain multiple blood samples at different hematocrit values and different blood glucose concentrations; Measure multiple sample current values and multiple sample detection values of the multiple blood samples; The current calibration equation is determined based on multiple sample current values and multiple sample detection values from multiple blood samples.
4. The method according to claim 1, characterized in that, The blood glucose test equation is determined using the following steps: Obtain multiple blood samples at multiple different blood glucose concentrations under multiple different hematocrit values, and obtain the actual hematocrit values of multiple blood samples; The blood glucose testing equation is determined by fitting multiple blood samples at different blood glucose concentrations and different hematocrit values, as well as the actual hematocrit values of the multiple blood samples. The blood glucose test equation includes a first coefficient and a second coefficient. The first coefficient is determined according to a first correction equation, and the second coefficient is determined according to a second correction equation.
5. The method according to claim 4, characterized in that, The first correction equation is determined by the following steps: Obtain multiple blood samples at multiple different blood glucose concentrations under multiple different hematocrit values, and obtain the actual hematocrit values of multiple blood samples; The first correction equation will be determined by fitting the hematocrit values of multiple blood samples, the blood glucose values of multiple blood samples, and the actual hematocrit values of multiple blood samples.
6. The method according to claim 5, characterized in that, The second correction equation is determined by the following steps: Obtain multiple blood samples at multiple different blood glucose concentrations under multiple different hematocrit values, and obtain the actual hematocrit values of multiple blood samples; The second correction equation is determined by fitting the hematocrit values of multiple blood samples, the blood glucose values of multiple blood samples, and the actual hematocrit values of multiple blood samples.
7. The method according to claim 4, characterized in that, The blood glucose test equation is: y = Cx + D; Where y is the blood glucose value of the blood to be tested, C is the first coefficient, D is the second coefficient, and x is the calibration current value.
8. The method according to claim 5, characterized in that, The first coefficient is determined by the following equation: C = A1H 2 +B1H+C1; Wherein, C is the first coefficient, H is the hematocrit value of the blood being tested, A1 is the first sub-coefficient, B1 is the second sub-coefficient, and C1 is the third sub-coefficient.
9. The method according to claim 6, characterized in that, The second coefficient is determined by the following equation: D = A²H 2 +B2H+C2; Where D is the second coefficient, H is the hematocrit value of the blood sample, A2 is the fourth sub-coefficient, B2 is the fifth sub-coefficient, and C2 is the sixth sub-coefficient.
10. A blood glucose meter, characterized in that, The blood glucose meter includes a processor (10), a memory (11), and a bus (12). The memory (11) stores machine-readable instructions executable by the processor (10). When the electronic device is running, the processor (10) communicates with the memory (11) via the bus (12). The processor (10) executes the machine-readable instructions to perform the steps of the method as described in any one of claims 1 to 9.