Blood glucose assessment method based on hematocrit compensation and related device

Abstract

The invention provides a blood glucose evaluation method based on hematocrit compensation and a related device, and the method comprises the steps: obtaining blood glucose reaction current and erythrocyte backlog background current at equal time intervals within the effective reaction time of test paper and a blood sample; determining a tap adjustment coefficient and a hematocrit compensation coefficient corresponding to the amplification voltage value and the erythrocyte backlog background current according to the blood glucose reaction current and the erythrocyte backlog background current; performing two-dimensional compensation calculation on the amplified voltage value to obtain a corrected voltage value; determining a final voltage value by adopting a weighted integral calculation mode according to the corrected voltage value; according to the final voltage value and a preset blood glucose concentration mapping function, the blood glucose value for hematocrit compensation is determined, the influence of multi-dimensional factors in the blood glucose reaction process can be comprehensively considered, the negative influence of interference factors such as hematocrit on the detection result is effectively eliminated, and the accuracy and reliability of blood glucose detection are remarkably improved.

Description

Technical Field

[0001] The present application relates to the field of medical equipment technology, and in particular to a blood glucose assessment method based on hematocrit compensation and related devices. Background Art

[0002] In the daily monitoring and management of diseases such as diabetes, blood glucose testing is a crucial link. It can help patients understand their blood glucose levels in a timely manner and provide a key basis for adjusting diet, exercise and drug treatment plans. At present, the existing blood glucose assessment method based on hematocrit compensation is mainly based on electrochemical method. The basic principle of this method is to use the enzyme on the test paper to undergo a specific chemical reaction with glucose in the blood to generate an electrical signal related to the blood glucose concentration. In specific operation, the blood sample is added to a special blood glucose test paper, and the test paper is connected to the blood glucose meter. The blood glucose meter promotes the chemical reaction on the test paper by applying a specific working voltage and detects the current signal generated during the reaction. Subsequently, the blood glucose meter converts the detected current signal into a blood glucose concentration value according to a pre-set algorithm, and finally displays the result on the instrument screen for the user to view.

[0003] However, existing detection methods fail to fully consider the impact of multi-dimensional factors such as hematocrit on the test results, and only rely on single-dimensional current data for calculations, resulting in less than ideal accuracy of the test results. This makes it difficult to meet the needs of application scenarios such as diabetes management that require high blood sugar detection accuracy. Summary of the Invention

[0004] The embodiments of the present application provide a blood glucose assessment method and related device based on hematocrit compensation, which can comprehensively consider the influence of multi-dimensional factors in the blood glucose response process, effectively eliminate the negative impact of interference factors such as hematocrit on the test results, and significantly improve the accuracy and reliability of blood glucose testing. It provides a more accurate basis for blood glucose monitoring and subsequent treatment plan formulation for diabetic patients, and has obvious advantages over traditional methods that only rely on single-dimensional data detection.

[0005] A first aspect of an embodiment of the present application provides a blood glucose assessment method based on hematocrit compensation, the method comprising: During the effective reaction time of the test strip and blood sample, the blood glucose response current is obtained at equal time intervals. and hematocrit background current ; According to the blood glucose response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor ; The amplified voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value ; According to the correction voltage value , the final voltage value is determined by weighted integral calculation ; According to the final voltage value and the preset blood glucose concentration mapping function to determine the hematocrit-compensated blood glucose value P.

[0006] In a possible implementation, the blood glucose reaction current is obtained at equal time intervals during the effective reaction time of the test strip and the blood sample. and hematocrit background current ,include: Time series after applying the first operating voltage , ,..., Collect blood glucose response current ; Time series after applying the second operating voltage , ,..., Collect hematocrit background current .

[0007] In a possible implementation, the blood glucose response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor ,include: The blood glucose response current is determined by using the first adaptive fitting curve data relationship table The corresponding voltage amplification factor ; According to the voltage amplification factor and blood glucose response current , determine the amplified voltage value ; The amplified voltage value is determined by using the second adaptive fitting curve data relationship table and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor .

[0008] In a possible implementation, the second adaptive fitting curve data relationship table is used to determine the amplified voltage value. and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor In the above, the hematocrit compensation coefficient The calculation formula is as follows: in, 、 is the quadratic compensation coefficient, is the hematocrit background current, is the baseline compensation constant.

[0009] In a possible implementation, the amplified voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value The calculation formula for the dual-dimensional compensation calculation is as follows: in, To correct the voltage value, is the tap adjustment coefficient, Amplify the voltage value, is the voltage fluctuation correction factor, is the hematocrit sensitivity coefficient, is the voltage change at adjacent time points, Hematocrit background current, It is the standard value of the background backlog of standard red blood cells.

[0010] In this example, the blood glucose response current and hematocrit background current are first accurately acquired at equal time intervals within the effective reaction time of the test strip and blood sample. This fully accounts for the changes in the current signal at different stages of the reaction process, providing a comprehensive data foundation for subsequent accurate calculations. Next, based on the acquired blood glucose response current and hematocrit background current, the correlation coefficients are determined using the first and second adaptive fitting curve data relationship tables, respectively, to accurately determine the amplified voltage value, the tap adjustment coefficient, and the hematocrit compensation coefficient. This adaptive fitting curve-based approach allows for flexible adjustments based on the actual conditions of different samples, improving the accuracy of parameter determination. A two-dimensional compensation calculation is then performed on the amplified voltage value to obtain a corrected voltage value, effectively reducing voltage deviations caused by interference from various factors such as hematocrit. A weighted integral calculation is then used based on the corrected voltage value to determine the final voltage value, further optimizing the voltage calculation process to more accurately reflect the actual blood glucose response. Finally, the hematocrit-compensated blood glucose value P is determined based on the final voltage value and a preset blood glucose concentration mapping function.

[0011] A second aspect of an embodiment of the present application provides a blood glucose assessment device based on hematocrit compensation, the device comprising: The acquisition unit is used to obtain the blood glucose reaction current at equal time intervals within the effective reaction time of the test strip and blood sample and hematocrit background current ; The first processing unit is used to process the blood sugar response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor ; The second processing unit is used to amplify the voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value ; The third processing unit is used to correct the voltage value according to the , the final voltage value is determined by weighted integral calculation ; A determining unit configured to determine the final voltage value according to the and the preset blood glucose concentration mapping function to determine the hematocrit-compensated blood glucose value P.

[0012] In a possible implementation, during the effective reaction time between the test strip and the blood sample, the blood glucose reaction current is obtained at equal time intervals. and hematocrit background current In the aspect, the acquisition unit is used to: Time series after applying the first operating voltage , ,..., Collect blood glucose response current ; Time series after applying the second operating voltage , ,..., Collect hematocrit background current .

[0013] In a possible implementation, according to the blood glucose response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor In the aspect, the first processing unit is configured to: The blood glucose response current is determined by using the first adaptive fitting curve data relationship table The corresponding voltage amplification factor ; According to the voltage amplification factor and blood glucose response current , determine the amplified voltage value ; The amplified voltage value is determined by using the second adaptive fitting curve data relationship table and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor .

[0014] In a possible implementation, the amplified voltage value is determined by using the second adaptive fitting curve data relationship table. and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor In the first processing unit, the hematocrit compensation coefficient The calculation formula is as follows: in, 、 is the quadratic compensation coefficient, is the hematocrit background current, is the baseline compensation constant.

[0015] In a possible implementation, in the amplified voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value In the aspect of the present invention, in the second processing unit, the calculation formula of the dual-dimensional compensation calculation is as follows: in, To correct the voltage value, is the tap adjustment coefficient, Amplify the voltage value, is the voltage fluctuation correction factor, is the hematocrit sensitivity coefficient, is the voltage change at adjacent time points, Hematocrit background current, It is the standard value of the background backlog of standard red blood cells.

[0016] A third aspect of an embodiment of the present application provides a terminal, comprising a processor, an input device, an output device, and a memory, wherein the processor, input device, output device, and memory are interconnected, wherein the memory is used to store a computer program, the computer program comprising program instructions, and the processor is configured to call the program instructions to execute the step instructions of the blood glucose assessment method based on hematocrit compensation as in the first aspect of the embodiment of the present application.

[0017] The fourth aspect of the embodiments of the present application provides a computer-readable storage medium, wherein the above-mentioned computer-readable storage medium stores a computer program for electronic data exchange, wherein the above-mentioned computer program enables a computer to execute part or all of the steps described in the blood glucose assessment method based on hematocrit compensation in the first aspect of the embodiments of the present application.

[0018] A fifth aspect of the embodiments of the present application provides a computer program product, wherein the computer program product includes a non-transitory computer-readable storage medium storing a computer program, wherein the computer program is operable to cause a computer to execute some or all of the steps described in the blood glucose assessment method based on hematocrit compensation in the first aspect of the embodiments of the present application. The computer program product may be a software installation package. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without any creative work.

[0020] Figure 1 A schematic diagram of the overall process of a blood glucose assessment method based on hematocrit compensation is provided for an embodiment of the present application; Figure 2 A schematic structural diagram of a blood glucose assessment device based on hematocrit compensation is provided for an embodiment of the present application; Figure 3 A schematic diagram of the structure of a terminal provided in an embodiment of the present application; Reference numerals: Acquisition unit-1, first processing unit-2, second processing unit-3, third processing unit-4, determination unit-5. DETAILED DESCRIPTION

[0021] The following will be combined with the drawings in the embodiments of this application to clearly and completely describe the technical solutions in the embodiments of this application. Obviously, the embodiments described are only part of the embodiments of this application, not all of the embodiments. Based on the embodiments in this application, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of this application.

[0022] The terms "first," "second," and the like in the specification and claims of this application and the accompanying drawings are used to distinguish between different objects, not to describe a particular order. Furthermore, the terms "including," "having," and any variations thereof, are intended to cover non-exclusive inclusions. For example, a process, method, system, product, or apparatus comprising a series of steps or elements is not limited to the listed steps or elements but may optionally include steps or elements not listed, or may optionally include other steps or elements inherent to the process, method, product, or apparatus.

[0023] References to "embodiments" in this application mean that a particular feature, structure, or characteristic described in connection with the embodiment may be included in at least one embodiment of the application. The appearance of this phrase in various places in the specification does not necessarily refer to the same embodiment, nor does it constitute an independent or alternative embodiment that is mutually exclusive of other embodiments. It is understood, both explicitly and implicitly, by those skilled in the art that the embodiments described in this application may be combined with other embodiments.

[0024] To better understand the blood glucose assessment method based on hematocrit compensation provided in the embodiments of this application, the following first briefly describes the application scenarios of this method. Existing blood glucose assessment methods based on hematocrit compensation primarily rely on single-dimensional data to determine blood glucose concentration. This means that the blood glucose value is estimated based solely on the current signal generated by a chemical reaction. In actual testing, the composition of a blood sample is relatively complex, containing not only glucose but also red blood cells, white blood cells, platelets, and other components. Among these, the hematocrit (HCT) is a factor that significantly influences test results. Hematocrit refers to the percentage of blood volume occupied by red blood cells. Hematocrit values ​​vary between individuals, and even within the same individual under different physiological conditions (e.g., before and after exercise, after a meal, etc.). When the hematocrit changes, it interferes with the chemical reaction process on the test strip and the transmission of the current signal, resulting in a deviation between the blood glucose value calculated solely based on the current signal and the actual blood glucose value.

[0025] The blood glucose assessment method based on hematocrit compensation is applied to a blood glucose assessment device based on hematocrit compensation. Figure 1 FIG. 1 shows a schematic diagram of the overall process of a blood glucose assessment method based on hematocrit compensation. Figure 1 Shown, including: S1. Obtain blood glucose response current at equal time intervals within the effective reaction time of the test strip and blood sample. and hematocrit background current .

[0026] In this example, when obtaining the blood glucose response current and hematocrit background current When the first working voltage is applied, the time series , ,..., Collect blood glucose response current ; Time series after applying the second operating voltage , ,..., Collect hematocrit background current .

[0027] S2, according to the blood sugar response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor .

[0028] S3, the amplified voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value .

[0029] S4, according to the correction voltage value , the final voltage value is determined by weighted integral calculation .

[0030] S5, according to the final voltage value and the preset blood glucose concentration mapping function to determine the hematocrit-compensated blood glucose value P.

[0031] Among them, during the effective period of the chemical reaction between the test paper and the blood sample, two types of signals are synchronously collected through time-sharing multiplexing electrode technology: in the time series t1, t2, ..., Apply a first working voltage to the glucose oxidase reaction electrode to obtain blood glucose reaction currents I1, I2, ..., ; At the same time, at staggered time points τ1, τ2,…, Apply the second working voltage to the hematocrit detection electrode and measure the background current H1, H2, ..., Based on the pre-stored dynamic parameter database, the blood glucose current is first mapped to the corresponding voltage amplification factor through the first adaptive fitting curve table to calculate the initial amplification voltage; then, the current and Query the second adaptive fitting curve table and output the tap adjustment coefficient and hematocrit compensation factor ,in pass , and the ratio of the reference value is dynamically calculated. Perform dual-dimensional compensation: First pass Correcting voltage gain nonlinearity, combined with Perform red blood cell interference compensation to eliminate signal deviation caused by differences in blood cell concentration and achieve high-precision measurement under complex physiological interference.

[0032] In this example, the blood glucose response current and hematocrit background current are first accurately acquired at equal time intervals within the effective reaction time of the test strip and blood sample. This fully accounts for the changes in the current signal at different stages of the reaction process, providing a comprehensive data foundation for subsequent accurate calculations. Next, based on the acquired blood glucose response current and hematocrit background current, the correlation coefficients are determined using the first and second adaptive fitting curve data relationship tables, respectively, to accurately determine the amplified voltage value, the tap adjustment coefficient, and the hematocrit compensation coefficient. This adaptive fitting curve-based approach allows for flexible adjustments based on the actual conditions of different samples, improving the accuracy of parameter determination. A two-dimensional compensation calculation is then performed on the amplified voltage value to obtain a corrected voltage value, effectively reducing voltage deviations caused by interference from various factors such as hematocrit. A weighted integral calculation is then used based on the corrected voltage value to determine the final voltage value, further optimizing the voltage calculation process to more accurately reflect the actual blood glucose response. Finally, the hematocrit-compensated blood glucose value P is determined based on the final voltage value and a preset blood glucose concentration mapping function.

[0033] In a possible implementation, the blood glucose response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor ,include: S201, using the first adaptive fitting curve data relationship table to determine the blood glucose response current The corresponding voltage amplification factor ; S202, according to the voltage amplification factor and blood glucose response current , determine the amplified voltage value ; S203, using the second adaptive fitting curve data relationship table to determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor .

[0034] Specifically, the second adaptive fitting curve data relationship table is used to determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor In the above, the hematocrit compensation coefficient The calculation formula is as follows: in, 、 is the quadratic compensation coefficient, is the hematocrit background current, is the baseline compensation constant.

[0035] Specifically, the amplified voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value The calculation formula for the dual-dimensional compensation calculation is as follows: in, To correct the voltage value, is the tap adjustment coefficient, Amplify the voltage value, is the voltage fluctuation correction factor, is the hematocrit sensitivity coefficient, is the voltage change at adjacent time points, Hematocrit background current, It is the standard value of the background backlog of standard red blood cells.

[0036] Dynamic signal optimization is achieved through a hierarchical parameter mapping mechanism. First, the real-time blood glucose response current collected is mapped to the corresponding voltage amplification factor using a pre-stored first adaptive fitting curve data relationship table. This data table, based on extensive experimental calibration of signal gain characteristics for different current ranges, adaptively adjusts the amplification factor based on the response intensity, effectively eliminating signal distortion caused by differences in test strip sensitivity. The voltage amplification factor is then multiplied by the real-time current value to obtain the initial amplified voltage, ensuring that the signal strength adapts to the dynamic range of the analog-to-digital converter. Furthermore, the amplified voltage value and the hematocrit background current are jointly analyzed using a second adaptive fitting curve data relationship table. This table utilizes multidimensional parameter space mapping technology to comprehensively consider the coupling effects of voltage nonlinear distortion and blood cell concentration interference. The output tap adjustment coefficient is used to correct circuit gain deviation, while the hematocrit compensation coefficient is generated to quantify the degree to which blood viscosity inhibits the electrochemical reaction. This hierarchical parameter matching mechanism breaks through the limitations of the traditional single compensation model, making it possible to accurately separate the target signal and interference components even in complex blood environments (such as pathological conditions such as hyperlipidemia and anemia). Measured data show that the hematocrit interference error can be reduced. At the same time, the linearity of the voltage signal is improved by dynamically adjusting the amplification parameters, providing high-fidelity input data for subsequent weighted integration and blood glucose value mapping, significantly improving the detection robustness under extreme physiological conditions.

[0037] In line with the above, please see Figure 2 , Figure 2 The present invention provides a schematic diagram of a structure of a device for determining a business product. Figure 2 As shown, the device includes: Acquisition unit 1 is used to obtain the blood glucose reaction current at equal time intervals within the effective reaction time of the test strip and blood sample and hematocrit background current ; The first processing unit 2 is used to process the blood sugar response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor ; The second processing unit 3 is used to amplify the voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value ; The third processing unit 4 is used to correct the voltage value according to the , the final voltage value is determined by weighted integral calculation ; Determining unit 5, for determining the final voltage value according to the and the preset blood glucose concentration mapping function to determine the hematocrit-compensated blood glucose value P.

[0038] In a possible implementation, during the effective reaction time between the test strip and the blood sample, the blood glucose reaction current is obtained at equal time intervals. and hematocrit background current In the aspect, the acquisition unit 1 is used to: Time series after applying the first operating voltage , ,..., Collect blood glucose response current ; Time series after applying the second operating voltage , ,..., Collect hematocrit background current .

[0039] In a possible implementation, according to the blood glucose response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor In the aspect, the first processing unit 2 is used to: The blood glucose response current is determined by using the first adaptive fitting curve data relationship table The corresponding voltage amplification factor ; According to the voltage amplification factor and blood glucose response current , determine the amplified voltage value ; The amplified voltage value is determined by using the second adaptive fitting curve data relationship table and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor .

[0040] In a possible implementation, the amplified voltage value is determined by using the second adaptive fitting curve data relationship table. and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor In the first processing unit 2, the hematocrit compensation coefficient The calculation formula is as follows: in, 、 is the quadratic compensation coefficient, is the hematocrit background current, is the baseline compensation constant.

[0041] In a possible implementation, in the amplified voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value In the aspect of the second processing unit 3, the calculation formula of the dual-dimensional compensation calculation is as follows: in, To correct the voltage value, is the tap adjustment coefficient, Amplify the voltage value, is the voltage fluctuation correction factor, is the hematocrit sensitivity coefficient, is the voltage change at adjacent time points, Hematocrit background current, It is the standard value of the background backlog of standard red blood cells.

[0042] For the same example as above, please refer to Figure 3 , Figure 3 A schematic structural diagram of a terminal provided in an embodiment of the present application, as shown in the figure, includes a processor, an input device, an output device, and a memory, the processor, the input device, the output device, and the memory being interconnected, wherein the memory is used to store a computer program, the computer program including program instructions, the processor being configured to call the program instructions, and the program including instructions for executing the following steps; During the effective reaction time of the test strip and blood sample, the blood glucose response current is obtained at equal time intervals. and hematocrit background current ; According to the blood glucose response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor ; The amplified voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value ; According to the correction voltage value , the final voltage value is determined by weighted integral calculation ; According to the final voltage value and the preset blood glucose concentration mapping function to determine the hematocrit-compensated blood glucose value P.

[0043] In this example, the blood glucose response current and hematocrit background current are first accurately acquired at equal time intervals within the effective reaction time of the test strip and blood sample. This fully accounts for the changes in the current signal at different stages of the reaction process, providing a comprehensive data foundation for subsequent accurate calculations. Next, based on the acquired blood glucose response current and hematocrit background current, the correlation coefficients are determined using the first and second adaptive fitting curve data relationship tables, respectively, to accurately determine the amplified voltage value, the tap adjustment coefficient, and the hematocrit compensation coefficient. This adaptive fitting curve-based approach allows for flexible adjustments based on the actual conditions of different samples, improving the accuracy of parameter determination. A two-dimensional compensation calculation is then performed on the amplified voltage value to obtain a corrected voltage value, effectively reducing voltage deviations caused by interference from various factors such as hematocrit. A weighted integral calculation is then used based on the corrected voltage value to determine the final voltage value, further optimizing the voltage calculation process to more accurately reflect the actual blood glucose response. Finally, the hematocrit-compensated blood glucose value P is determined based on the final voltage value and a preset blood glucose concentration mapping function.

[0044] The above mainly introduces the scheme of the embodiment of the present application from the perspective of the execution process on the method side. It is understandable that, in order to implement the above functions, the terminal includes hardware structures and / or software modules corresponding to the execution of each function. Those skilled in the art should easily realize that, in combination with the units and algorithm steps of the various examples described in the embodiments provided herein, the present application can be implemented in the form of hardware or a combination of hardware and computer software. Whether a function is executed in a hardware or computer software driven hardware manner depends on the specific application and design constraints of the technical solution. Professional and technical personnel can use different methods to implement the described functions for each specific application, but such implementation should not be considered to be beyond the scope of this application.

[0045] The embodiment of the present application can divide the terminal into functional units according to the above method example. For example, each functional unit can be divided according to each function, or two or more functions can be integrated into one processing unit. The above integrated unit can be implemented in the form of hardware or in the form of software functional units. It should be noted that the division of units in the embodiment of the present application is schematic and is only a logical functional division. In actual implementation, there may be other division methods.

[0046] An embodiment of the present application also provides a computer storage medium, wherein the computer storage medium stores a computer program for electronic data exchange, and the computer program enables a computer to execute part or all of the steps of any one of the blood glucose assessment methods based on hematocrit compensation as described in the above method embodiments.

[0047] An embodiment of the present application also provides a computer program product, which includes a non-transitory computer-readable storage medium storing a computer program, and the computer program enables a computer to execute part or all of the steps of any one of the blood glucose assessment methods based on hematocrit compensation as described in the above method embodiments.

[0048] It should be noted that for the aforementioned method embodiments, for the sake of simplicity, they are all expressed as a series of action combinations, but those skilled in the art should be aware that this application is not limited by the order of the actions described, because according to this application, certain steps can be performed in other orders or simultaneously. Secondly, those skilled in the art should also be aware that the embodiments described in the specification are all preferred embodiments, and the actions and modules involved are not necessarily required by this application.

[0049] In the above embodiments, the description of each embodiment has its own focus. For parts that are not described in detail in a certain embodiment, reference can be made to the relevant descriptions of other embodiments.

[0050] In the several embodiments provided in this application, it should be understood that the disclosed devices can be implemented in other ways. For example, the device embodiments described above are merely illustrative. For example, the division of the units is merely a logical function division. In actual implementation, there may be other division methods, such as multiple units or components can be combined or integrated into another system, or some features can be ignored or not executed. Another point is that the mutual coupling or direct coupling or communication connection shown or discussed can be through some interfaces, and the indirect coupling or communication connection of devices or units can be electrical or other forms.

[0051] The units described as separate components may or may not be physically separate, and 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 these units may be selected to achieve the purpose of this embodiment according to actual needs.

[0052] In addition, the functional units in the various embodiments of the application may be integrated into a single processing unit, or each unit may exist physically separately, or two or more units may be integrated into a single unit. The aforementioned integrated units may be implemented in the form of hardware or software program modules.

[0053] If the integrated unit is implemented in the form of a software program module and sold or used as an independent product, it can be stored in a computer-readable memory. Based on this understanding, the technical solution of the present application, or the part that contributes to the prior art, or all or part of the technical solution can be embodied in the form of a software product. The computer software product is stored in a memory and includes a number of instructions for enabling a computer device (which can be a personal computer, server or network device, etc.) to execute all or part of the steps of the method described in each embodiment of the present application. The aforementioned memory includes: U disk, read-only memory (ROM), random access memory (RAM), mobile hard disk, magnetic disk or optical disk, and other media that can store program code.

[0054] Those skilled in the art will understand that all or part of the steps in the various methods of the above embodiments can be completed by instructing related hardware through a program, and the program can be stored in a computer-readable memory, which may include: a flash drive, a read-only memory, a random access memory, a magnetic disk or an optical disk, etc.

[0055] The above is a detailed introduction to the embodiments of the present application. Specific examples are used herein to illustrate the principles and implementation methods of the present application. The description of the above embodiments is only used to help understand the method and core idea of ​​the present application. At the same time, for those skilled in the art, according to the idea of ​​the present application, there may be changes in the specific implementation methods and application scope. In summary, the content of this specification should not be understood as a limitation on the present application.

Claims

1. A blood glucose assessment method based on hematocrit compensation, characterized in that: include: During the effective reaction time of the test strip and blood sample, the blood glucose response current is obtained at equal time intervals. and hematocrit background current ; According to the blood glucose response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor ; The amplified voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value ; According to the correction voltage value , the final voltage value is determined by weighted integral calculation ; According to the final voltage value and the preset blood glucose concentration mapping function to determine the hematocrit-compensated blood glucose value P.

2. The blood glucose assessment method based on hematocrit compensation according to claim 1, characterized in that: The blood glucose reaction current is obtained at equal time intervals within the effective reaction time of the test strip and the blood sample. and hematocrit background current ,include: Time series after applying the first operating voltage , ,..., Collect blood glucose response current ; Time series after applying the second operating voltage , ,..., Collect hematocrit background current .

3. The blood glucose assessment method based on hematocrit compensation according to claim 1, characterized in that: The blood glucose response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor ,include: The blood glucose response current is determined by using the first adaptive fitting curve data relationship table The corresponding voltage amplification factor ; According to the voltage amplification factor and blood glucose response current , determine the amplified voltage value ; The amplified voltage value is determined by using the second adaptive fitting curve data relationship table and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor .

4. The blood glucose assessment method based on hematocrit compensation according to claim 3, characterized in that: The second adaptive fitting curve data relationship table is used to determine the amplified voltage value. and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor In the above, the hematocrit compensation coefficient The calculation formula is as follows: in, 、 is the quadratic compensation coefficient, is the hematocrit background current, is the baseline compensation constant.

5. The blood glucose assessment method based on hematocrit compensation according to claim 1, characterized in that: The amplified voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value The calculation formula for the dual-dimensional compensation calculation is as follows: in, To correct the voltage value, is the tap adjustment coefficient, Amplify the voltage value, is the voltage fluctuation correction factor, is the hematocrit sensitivity coefficient, is the voltage change at adjacent time points, Hematocrit background current, It is the standard value of the background backlog of standard red blood cells.

6. A blood glucose assessment device based on hematocrit compensation, characterized in that: The device comprises: The acquisition unit is used to obtain the blood glucose reaction current at equal time intervals within the effective reaction time of the test strip and blood sample and hematocrit background current ; The first processing unit is used to process the blood sugar response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor ; The second processing unit is used to amplify the voltage value Perform two-dimensional compensation calculation to obtain the corrected voltage value ; The third processing unit is used to correct the voltage value according to the , the final voltage value is determined by weighted integral calculation ; A determining unit configured to determine the final voltage value according to the and the preset blood glucose concentration mapping function to determine the hematocrit-compensated blood glucose value P.

7. The blood glucose assessment device based on hematocrit compensation according to claim 6, characterized in that: During the effective reaction time between the test strip and the blood sample, the blood glucose reaction current is obtained at equal time intervals. and hematocrit background current In the aspect, the acquisition unit is used to: Time series after applying the first operating voltage , ,..., Collect blood glucose response current ; Time series after applying the second operating voltage , ,..., Collect hematocrit background current .

8. The blood glucose assessment device based on hematocrit compensation according to claim 6, characterized in that: In the blood glucose response current and hematocrit background current , determine the amplified voltage value and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor In the aspect, the first processing unit is configured to: The blood glucose response current is determined by using the first adaptive fitting curve data relationship table The corresponding voltage amplification factor ; According to the voltage amplification factor and blood glucose response current , determine the amplified voltage value ; The amplified voltage value is determined by using the second adaptive fitting curve data relationship table and the hematocrit background current Corresponding tap adjustment coefficient and hematocrit compensation factor .

9. A terminal, characterized in that: The method comprises a processor, an input device, an output device and a memory, wherein the processor, the input device, the output device and the memory are interconnected, wherein the memory is used to store a computer program, the computer program includes program instructions, and the processor is configured to call the program instructions to execute the blood glucose assessment method based on hematocrit compensation according to any one of claims 1 to 5.

10. A computer-readable storage medium, characterized in that The computer-readable storage medium stores a computer program, which includes program instructions. When the program instructions are executed by a processor, the processor executes the blood glucose assessment method based on hematocrit compensation according to any one of claims 1 to 5.

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