Electrochemical method, device, apparatus and medium for blood detection

Abstract

The application discloses an electrochemical detection method, device, equipment and medium for blood, and relates to the technical field of medical detection. The method comprises the following steps: obtaining initial current values of target analytes in a blood sample to be detected at each time point based on a preset time interval and by using an electrochemical biosensor; obtaining a current curve area value by using the initial current values, screening target current values in different preset time periods from the initial current values, performing weighted summation on the target current values to obtain a weighted current value; determining a current characteristic value by summing the current curve area value and the weighted current value; and determining a concentration result of the target analyte by using a concentration prediction formula and the current characteristic value. By the above scheme, the current characteristic value is obtained according to the initial current values at each time point, and the oxygen interference in blood can be reduced to realize more accurate blood detection.

Description

Technical Field

[0001] This invention relates to the field of medical testing technology, and in particular to electrochemical detection methods, devices, equipment and media for blood. Background Technology

[0002] In recent years, disposable electrochemical test strips prepared using screen printing technology have been widely used in the field of point-of-care testing. The reaction principle is mainly based on electron transfer following a reaction between reagents with redox properties. Potassium ferricyanide (KF) is inexpensive and highly reactive, and is commonly used as an electron transfer agent for measuring blood glucose, blood ketones, and blood lipids. However, its use as an electron transfer agent easily triggers reactions with interfering substances in the blood, leading to measurement errors. Furthermore, degradation caused by temperature and humidity necessitates careful manufacturing and storage of the test strips. Compared to KF, hexaammonium trichloride (HJT) exhibits better redox stability. Sensors using HJT as an electron transfer agent can be easily manufactured and stored, and exhibit minimal current changes after long-term storage. However, HJT alone has too low an electron transfer efficiency for commercial use; therefore, a second electron transfer agent must be added. Currently, commonly used second electron transfer agents include methyl 5-methylphenazine sulfate, ethyl 5-ethylphenazine sulfate, and methyl 1-methoxy-5-methylphenazine sulfate. Due to the highly reactive nature of the second electron mediator, the interference effect of oxygen in the blood on the measurement is prominent, especially when the hematocrit is high and the analyte concentration is very low. The presence of this interference effect directly affects the analytical sensitivity of the sensor.

[0003] In summary, reducing oxygen interference in the blood to achieve more accurate blood testing is a problem that needs to be solved in this field. Summary of the Invention

[0004] In view of this, the purpose of this invention is to provide an electrochemical detection method, apparatus, device, and medium for blood, reducing oxygen interference in the blood to achieve more accurate blood detection. The specific solution is as follows:

[0005] In a first aspect, this application discloses an electrochemical detection method for blood, comprising:

[0006] Based on a preset time interval, the initial current value of the target analyte in the blood sample to be tested at each time point is obtained using an electrochemical biosensor;

[0007] The area of ​​the current curve is obtained using the initial current value, and target current values ​​for different preset time periods are selected from each initial current value. The target current values ​​are then weighted and summed to obtain the weighted current value.

[0008] The sum of the area under the current curve and the weighted current value is determined as the current characteristic value;

[0009] The concentration of the target analyte is determined using the concentration prediction formula and the current characteristic value.

[0010] Optionally, the electron mediator in the electrochemical biosensor includes a first electron mediator and a second electron mediator, wherein the first electron mediator is hexaammonium trichloride ruthenium chloride, and the second electron mediator is any one of methyl 5-methylphenazine sulfate, ethyl 5-ethylphenazine sulfate, and methyl 1-methoxy-5-methylphenazine sulfate.

[0011] Optionally, obtaining the area under the current curve using the initial current value includes:

[0012] A scatter plot is plotted using each of the initial current values ​​to obtain the current curve of the blood sample to be tested.

[0013] use Calculate the area under the current curve; where A represents the area under the current curve, t represents the preset time interval, i represents the starting index of the initial current value, k represents the preset empirical value, n represents the ending index of the initial current value, and I represents the initial current value.

[0014] Optionally, the preset empirical value can be in the range of 3 to 5.

[0015] Optionally, the step of selecting target current values ​​for different preset time periods from the initial current values ​​and performing a weighted summation on the target current values ​​to obtain a weighted current value includes:

[0016] Select a first target current value for a first preset time period, a second target current value for a second preset time period, and a third target current value for a third preset time period from the initial current values.

[0017] The first target current value, the second target current value, and the third target current value are weighted and summed using a second preset formula to obtain a weighted current value.

[0018] Optionally, the step of using a second preset formula to perform a weighted summation of the first target current value, the second target current value, and the third target current value to obtain a weighted current value includes:

[0019] Using B = xI a +yI b +zI c The first target current value, the second target current value, and the third target current value are weighted and summed to obtain a weighted current value; where Ia I represents the first target current value. b I represents the second target current value. c Let x represent the first target current value, y represent the second target current value, z represent the third target current value, and B represent the weighted current value.

[0020] Optionally, the first preset time period is the early stage of the acquisition cycle of the initial current value, the second preset time period is the middle stage of the acquisition cycle, and the third preset time period is the late stage of the acquisition cycle.

[0021] Optionally, the sum of the first weighting coefficient, the second weighting coefficient, and the third weighting coefficient is 1, wherein the first weighting coefficient is greater than 60%, the second weighting coefficient is greater than 15% and less than 25%, and the third weighting coefficient is greater than 5% and less than 15%.

[0022] Optionally, before determining the concentration of the target analyte using the concentration prediction formula and the current characteristic value, the method further includes:

[0023] Determine the concentration of historical analytes in each historical blood sample, and obtain the historical current characteristic value of each historical analyte concentration;

[0024] A concentration prediction formula is derived by fitting the historical current characteristic values ​​and the historical analyte concentrations.

[0025] Secondly, this application discloses an electrochemical detection device for blood, comprising:

[0026] The first current acquisition module is used to acquire the initial current value of the target analyte in the blood sample to be tested at each time point based on a preset time interval and using an electrochemical biosensor.

[0027] The second current acquisition module is used to acquire the area value of the current curve using the initial current value, and to filter out target current values ​​for different preset time periods from each initial current value, and to perform a weighted summation on each target current value to obtain a weighted current value.

[0028] The feature value acquisition module is used to determine the sum of the current curve area value and the weighted current value as the current feature value;

[0029] The concentration result prediction module is used to determine the concentration result of the target analyte using the concentration prediction formula and the current characteristic value.

[0030] Thirdly, this application discloses an electronic device, including:

[0031] Memory, used to store computer programs;

[0032] A processor for executing the computer program to implement the steps of the aforementioned disclosed electrochemical detection method for blood.

[0033] Fourthly, this application discloses a computer-readable storage medium for storing a computer program; wherein, when the computer program is executed by a processor, it implements the steps of the aforementioned disclosed electrochemical detection method for blood.

[0034] The beneficial effects of this application are as follows: This application acquires the initial current value of the target analyte in the blood sample at various times based on a preset time interval and using an electrochemical biosensor; it obtains the area under the current curve using the initial current value, and selects target current values ​​for different preset time periods from the initial current values, and performs a weighted summation of the target current values ​​to obtain a weighted current value; the sum of the area under the current curve and the weighted current value is determined as the current characteristic value; and the concentration of the target analyte is determined using a concentration prediction formula and the current characteristic value. Because different oxygen partial pressures at the same analyte concentration will result in different current values, leading to discrepancies in the final predicted analyte concentration, this application acquires the initial current value at various times, and then obtains the area under the current curve and the weighted current value after weighting for different preset time periods based on each initial current value, thereby determining a more accurate current characteristic value. Therefore, the concentration result of the target analyte determined using the concentration prediction formula and the current characteristic value is more accurate and reduces the interference of oxygen partial pressure. Attached Figure Description

[0035] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on the provided drawings without creative effort.

[0036] Figure 1 This is a flowchart of an electrochemical detection method for blood disclosed in this application;

[0037] Figure 2 This is a schematic diagram illustrating a specific blood testing accuracy comparison disclosed in this application;

[0038] Figure 3 This is a schematic diagram of fitting a specific concentration calculation equation disclosed in this application;

[0039] Figure 4 This is a schematic diagram of fitting a specific concentration prediction formula disclosed in this application;

[0040] Figure 5 This is a schematic diagram of the structure of an electrochemical detection device for blood disclosed in this application;

[0041] Figure 6 This is a structural diagram of an electronic device disclosed in this application. Detailed Implementation

[0042] 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 the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the scope of protection of the present invention.

[0043] In recent years, disposable electrochemical test strips prepared using screen printing technology have been widely used in the field of point-of-care testing. The reaction principle is mainly based on electron transfer following a reaction between reagents with redox properties. Potassium ferricyanide (KF) is inexpensive and highly reactive, and is commonly used as an electron transfer agent for measuring blood glucose, blood ketones, and blood lipids. However, its susceptibility to reacting with interfering substances in the blood, leading to measurement errors, and its degradation due to temperature and humidity necessitate careful manufacturing and storage of the test strips. Compared to KF, hexaammonium trichloride (HJT) exhibits better redox stability. Sensors using HJT as an electron transfer agent can be easily manufactured and stored, with minimal current change after long-term storage. However, HJT alone has too low an electron transfer efficiency for commercial use; therefore, a second electron transfer agent must be added. Currently, commonly used second electron transfer agents include methyl 5-methylphenazine sulfate, ethyl 5-ethylphenazine sulfate, and methyl 1-methoxy-5-methylphenazine sulfate. Due to the highly reactive nature of the second electron mediator, the interference effect of oxygen in the blood on the measurement is prominent, especially when the hematocrit is high and the analyte concentration is very low. The presence of this interference effect directly affects the analytical sensitivity of the sensor.

[0044] Therefore, this application provides a blood testing solution that reduces oxygen interference in the blood to achieve more accurate blood testing.

[0045] See Figure 1 As shown in the embodiments, this application discloses an electrochemical detection method for blood, including:

[0046] Step S11: Based on a preset time interval, the initial current value of the target analyte in the blood sample to be tested is obtained at each time point using an electrochemical biosensor;

[0047] In this embodiment, the electron mediator in the electrochemical biosensor includes a first electron mediator and a second electron mediator. The first electron mediator is hexaammonium trichloride ruthenium chloride, and the second electron mediator is any one of methyl 5-methylphenazine sulfate, ethyl 5-ethylphenazine sulfate, and methyl 1-methoxy-5-methylphenazine sulfate. The electrochemical biosensor includes an enzyme solution, a hematocrit measurement electrode, a working electrode, a reference electrode (counter electrode), the first electron mediator, and the second electron mediator. The first electron mediator is hexaammonium trichloride ruthenium chloride, and the second electron mediator is any one of methyl 5-methylphenazine sulfate, ethyl 5-ethylphenazine sulfate, and methyl 1-methoxy-5-methylphenazine sulfate. The enzyme solution covers the surface area of ​​the working electrode.

[0048] A blood detection circuit is constructed using a working electrode and a reference electrode covered with a biorecognition enzyme. The working electrode covered with the biorecognition enzyme is then brought into contact with the blood sample to be tested. The target analyte in the blood sample reacts chemically with the biorecognition enzyme. The target analyte may be, for example, β-hydroxybutyrate (a blood ketone indicator), glucose, cholesterol, or triglycerides.

[0049] A voltage is applied to the working electrode to obtain the response current of the target analyte, and timing begins. Current values ​​are recorded at preset time intervals, i.e., the initial current value of the target analyte at each moment is obtained. For example, from second 0 to second 6, an initial current value is recorded every 0.1 seconds, resulting in 60 initial current values. These 60 initial current values ​​are then assigned sequence numbers based on their time order, i.e., I1, I2, ..., I... 59 ,I 60 .

[0050] Step S12: Obtain the area of ​​the current curve using the initial current value, and select target current values ​​for different preset time periods from each initial current value. Perform a weighted summation on each target current value to obtain a weighted current value.

[0051] In this embodiment, obtaining the area of ​​the current curve using the initial current value includes: plotting a scatter plot using each of the initial current values ​​to obtain the current curve of the blood sample to be tested; using... Calculate the area under the current curve; where A represents the area under the current curve, t represents the preset time interval, i represents the starting index of the initial current value, k represents the preset empirical value, n represents the ending index of the initial current value, and I represents the initial current value. Establish a scatter plot in a coordinate system with the time T for recording the initial current value as the abscissa and the current value as the ordinate to obtain the current curve of the blood sample to be tested. Then, calculate the area under the current curve A using the first preset formula. Utilize the current trend characteristics of the initial reaction and the later stages of the reaction under different oxygen partial pressures to calculate the sum of the current areas, i.e., the area under the current curve. For example, if k = 3, n = 60, i = 1, and t = 0.1, then the first preset formula is specifically:

[0052]

[0053] In this embodiment, the preset empirical value ranges from 3 to 5. Because the initial signal of the electrochemical reaction exhibits significant instability, the first few current signals are discarded during calculation. Therefore, a k value is added, which is a natural number and can range from 3 to 5, or take other values ​​determined empirically.

[0054] In this embodiment, the step of selecting target current values ​​for different preset time periods from each of the initial current values ​​and performing a weighted summation on each of the target current values ​​to obtain a weighted current value includes: selecting a first target current value for a first preset time period, a second target current value for a second preset time period, and a third target current value for a third preset time period from each of the initial current values; and performing a weighted summation on the first target current value, the second target current value, and the third target current value using a second preset formula to obtain a weighted current value.

[0055] In this embodiment, the step of using a second preset formula to perform a weighted summation of the first target current value, the second target current value, and the third target current value to obtain a weighted current value includes: using B = xI a +yI b +zI c The first target current value, the second target current value, and the third target current value are weighted and summed to obtain a weighted current value; where I a I represents the first target current value. b I represents the second target current value. crepresents the third target current value, x represents the first weighting coefficient of the first target current value, y represents the second weighting coefficient of the second target current value, z represents the third weighting coefficient of the third target current value, and B represents the weighted current value. For example, the first target current value is I4, it should be noted that it is preferable to select a current signal with an earlier sequence number but not the initial current signal, and the second target current value is I 32 , the third target current value is I 60 .

[0056] In this embodiment, the first preset time period is an early period within the acquisition cycle of the initial current value, the second preset time period is a middle period within the acquisition cycle, and the third preset time period is a late period within the acquisition cycle. The first target current value is a current value within an earlier time period (i.e., the first preset time period) in the current value acquisition cycle, for example, a certain current signal within the 1st second or the 2nd second, that is, from I1 to I 20 for selection; the second target current value is a current value within a middle time period (i.e., the second preset time period) in the current value acquisition cycle, for example, a certain current signal within the 3rd second or the 4th second, from I 21 to I 40 for optional selection; the third target current value is a current value within a later time period (i.e., the third preset time period) in the current value acquisition cycle, for example, a certain current signal within the 5th second or the 6th second, from I 41 to I 60 for optional selection.

[0057] In this embodiment, the sum of the first weighting coefficient, the second weighting coefficient and the third weighting coefficient is 1, wherein the first weighting coefficient is greater than 60%, the second weighting coefficient is greater than 15% and less than 25%, and the third weighting coefficient is greater than 5% and less than 15%. x, y and z are all weight percentages, x+y+z=1 and x satisfies x>60%, preferably 70%, y satisfies 15%<y<25%, preferably 20%, z satisfies 5%<z<15%, preferably 10%.

[0058] Step S13: determining the sum of the current curve area value and the weighted current value as a current characteristic value.

[0059] The sum of the current curve area value and the weighted current value is determined as a current characteristic value, and the summation formula is specifically as follows:

[0060] Current characteristic value = A + B.

[0061] Step S14: determining the concentration result of the target analyte by using a concentration prediction formula and the current characteristic value.

[0062] In this embodiment, before determining the concentration of the target analyte using the concentration prediction formula and the current characteristic value, the method further includes: determining the historical analyte concentration in each historical blood sample and obtaining the historical current characteristic value of each historical analyte concentration; and fitting the concentration prediction formula using each historical current characteristic value and the historical analyte concentration. The concentration prediction formula uses the current characteristic value as the independent variable, and the specific concentration prediction formula is as follows:

[0063] C = S * current characteristic value + b;

[0064] In the formula, C represents the concentration of the target analyte, S represents the slope, and b represents the intercept.

[0065] The beneficial effects of this application are as follows: This application acquires the initial current value of the target analyte in the blood sample at various times based on a preset time interval and using an electrochemical biosensor; it obtains the area under the current curve using the initial current value, and selects target current values ​​for different preset time periods from the initial current values, and performs a weighted summation of the target current values ​​to obtain a weighted current value; the sum of the area under the current curve and the weighted current value is determined as the current characteristic value; and the concentration of the target analyte is determined using a concentration prediction formula and the current characteristic value. Because different oxygen partial pressures at the same analyte concentration will result in different current values, leading to discrepancies in the final predicted analyte concentration, this application acquires the initial current value at various times, and then obtains the area under the current curve and the weighted current value after weighting for different preset time periods based on each initial current value, thereby determining a more accurate current characteristic value. Therefore, the concentration result of the target analyte determined using the concentration prediction formula and the current characteristic value is more accurate and reduces the interference of oxygen partial pressure.

[0066] The following section uses blood ketone as an example to explain how the concentration prediction formula of this application was obtained.

[0067] 1) Sample Preparation: Samples were prepared according to gradients of blood ketone concentration and oxygen partial pressure. Specifically, five blood ketone concentrations were used to prepare five samples: S1 (blood ketone biochemical measurement value of 0.34 mmol / L), S2 (blood ketone biochemical measurement value of 1.18 mmol / L), S3 (blood ketone biochemical measurement value of 2.27 mmol / L), S4 (blood ketone biochemical measurement value of 3.79 mmol / L), and S5 (blood ketone biochemical measurement value of 5.40 mmol / L). The biochemical measurements were used as reference values ​​for the concentration of blood ketone analytes. The oxygen partial pressures of these five samples were adjusted (e.g., 20 mmHg, 70 mmHg, 100 mmHg, and 180 mmHg), resulting in a total of 20 samples (S=20) including S11-S14, S21-S24, S31-S34, S41-S44, and S51-S54. The total number of samples can also be adjusted according to actual needs, as long as the two indicators of analyte concentration and oxygen partial pressure can cover the low, medium and high ranges.

[0068] 2) Recording the current signal (i.e., the initial current value): Using the corresponding blood ketone testing system, i.e., the blood ketone analyzer and its matching test strips, the first electron mediator in the test strips is configured with hexaammonium trichloride ruthenium chloride and the second electron mediator phase. The 20 samples were tested separately. The test started at a fixed preset interval t = 0.1 seconds and ended at a certain second when the signal began to plateau (e.g., the 6th second after the start of the test; the time for signal plateauing varies for different analytes). The current signal (nA) within this time period T (from the start of sample injection to the 6th second, T = 6s) was recorded. Each sample generated 60 current signals in chronological order, and the current signal numbers were I1, I2…I… 60 In other words, there will be 20 samples, and each sample will have 60 current signals. Understandably, the preset interval t can be adjusted according to different preferences, such as choosing different time intervals like 0.2 seconds or 0.5 seconds. The total duration T varies depending on the analyte, and the total number of current signals for each sample is n = T / t.

[0069] 3) Data calculation: With time T as the x-axis and the current value of each sample as the y-axis, a scatter plot is built in the coordinate system to obtain the current curve of each sample. The area of ​​the current curve A and the weighted current value B for the specified time period are calculated. The current characteristic value is calculated, where the current characteristic value = A + B. In this way, the number of current characteristic values ​​is also 20, that is, the current characteristic values ​​corresponding to 20 samples can be obtained.

[0070] 4) Concentration prediction formula fitting: The concentration prediction formula is obtained by fitting multiple pairs of current characteristic values ​​with blood ketone concentration (biochemical value).

[0071] For example Figure 2This diagram illustrates a comparison of specific blood test accuracy. Figure 2 The left side shows existing electrochemical detection methods for blood, which generally use a current value for each sample during the plateau phase of the reaction current (e.g., the last current value I). 60 The concentration calculation equation is obtained by directly fitting the sample concentration (biochemical value), such as... Figure 3 The diagram shows a specific concentration calculation equation fitting schematic. The horizontal axis represents the current value, and the vertical axis represents the biochemical concentration value. In the actual measurement process, the current value at the same node (the same time node selected for equation fitting) is substituted into the concentration calculation equation to calculate the analyte concentration (predicted value), as well as the corresponding deviation calculation and the comprehensive deviation of the same concentration. Figure 2 The right side illustrates the electrochemical detection method for blood in this embodiment. The calculated current characteristic value is fitted to the sample concentration (biochemical value) to obtain the concentration calculation equation, as shown below. Figure 4 The diagram illustrates a specific concentration prediction formula fitting process, with the horizontal axis representing the current characteristic value and the vertical axis representing the biochemical concentration value. During actual testing, the current characteristic value calculated using the same method is substituted into the concentration calculation equation to calculate the analyte concentration (predicted value), along with the corresponding deviation calculation and the overall deviation for the same concentration. This comparison reveals that the deviation of the blood electrochemical detection method in this embodiment is relatively low, especially at the low-value end (lower analyte concentration), demonstrating that this proposal can solve the interference problem caused by oxygen partial pressure at the low-value end and improve the accuracy of the test.

[0072] See Figure 5 As shown in the figure, this application discloses an electrochemical detection device for blood, comprising:

[0073] The first current acquisition module 11 is used to acquire the initial current value of the target analyte in the blood sample to be tested at each time point based on a preset time interval and using an electrochemical biosensor.

[0074] The second current acquisition module 12 is used to acquire the area value of the current curve using the initial current value, and to select target current values ​​for different preset time periods from each initial current value, and to perform a weighted summation on each target current value to obtain a weighted current value.

[0075] The feature value acquisition module 13 is used to determine the sum of the current curve area value and the weighted current value as the current feature value;

[0076] The concentration result prediction module 14 is used to determine the concentration result of the target analyte using the concentration prediction formula and the current characteristic value.

[0077] The beneficial effects of this application are as follows: This application involves contacting a working electrode covered with a biorecognition enzyme with the blood sample to be tested; applying a voltage to the working electrode to obtain the initial current value of the target analyte in the blood sample at various times based on a preset time interval; using the initial current value to obtain the area of ​​the current curve, and selecting target current values ​​for different preset time periods from the initial current values, and weighting and summing the target current values ​​to obtain a weighted current value; determining the sum of the area of ​​the current curve and the weighted current value as the current characteristic value; and using the concentration prediction formula and the current characteristic value to determine the concentration result of the target analyte. Because different oxygen partial pressures at the same analyte concentration will result in different current values, leading to differences in the final predicted analyte concentration, this application obtains the initial current value at various times, and then obtains the area of ​​the current curve and the weighted current value after weighting for different preset time periods based on the initial current value, thereby determining a more accurate current characteristic value. Therefore, the concentration result of the target analyte determined by the concentration prediction formula and the current characteristic value is more accurate and reduces the interference of oxygen partial pressure.

[0078] Furthermore, embodiments of this application also provide an electronic device. Figure 6 This is a structural diagram of an electronic device 20 according to an exemplary embodiment. The content of the diagram should not be construed as limiting the scope of this application.

[0079] Figure 6 This is a schematic diagram of the structure of an electronic device provided in an embodiment of this application. Specifically, it may include: at least one processor 21, at least one memory 22, a power supply 23, a communication interface 24, an input / output interface 25, and a communication bus 26. The memory 22 stores a computer program, which is loaded and executed by the processor 21 to implement the following steps:

[0080] In some specific embodiments, the processor executes a computer program stored in the memory, specifically implementing the following steps:

[0081] The electron mediator in the electrochemical biosensor includes a first electron mediator and a second electron mediator. The first electron mediator is hexaammonium trichloride ruthenium trichloride, and the second electron mediator is any one of methyl 5-methylphenazine sulfate, ethyl 5-ethylphenazine sulfate, and methyl 1-methoxy-5-methylphenazine sulfate.

[0082] In some specific embodiments, the processor executes a computer program stored in the memory, specifically implementing the following steps:

[0083] A scatter plot is plotted using each of the initial current values ​​to obtain the current curve of the blood sample to be tested;

[0084] use Calculate the area under the current curve; where A represents the area under the current curve, t represents the preset time interval, i represents the starting index of the initial current value, k represents the preset empirical value, n represents the ending index of the initial current value, and I represents the initial current value.

[0085] In some specific embodiments, the processor executes a computer program stored in the memory, specifically implementing the following steps:

[0086] The preset experience value ranges from 3 to 5.

[0087] In some specific embodiments, the processor executes a computer program stored in the memory, specifically implementing the following steps:

[0088] The step of selecting target current values ​​for different preset time periods from each of the initial current values ​​and performing a weighted summation of the target current values ​​to obtain a weighted current value includes:

[0089] Select a first target current value for a first preset time period, a second target current value for a second preset time period, and a third target current value for a third preset time period from the initial current values.

[0090] The first target current value, the second target current value, and the third target current value are weighted and summed using a second preset formula to obtain a weighted current value.

[0091] In some specific embodiments, the processor executes a computer program stored in the memory, specifically implementing the following steps:

[0092] The step of using a second preset formula to perform a weighted summation of the first target current value, the second target current value, and the third target current value to obtain a weighted current value includes:

[0093] Using B = xI a +yI b +zI c The first target current value, the second target current value, and the third target current value are weighted and summed to obtain a weighted current value; where I a I represents the first target current value. b I represents the second target current value. cLet x represent the first target current value, y represent the second target current value, z represent the third target current value, and B represent the weighted current value.

[0094] In some specific embodiments, the processor executes a computer program stored in the memory, specifically implementing the following steps:

[0095] The first preset time period is the early stage of the acquisition cycle of the initial current value, the second preset time period is the middle stage of the acquisition cycle, and the third preset time period is the late stage of the acquisition cycle.

[0096] In some specific embodiments, the processor executes a computer program stored in the memory, specifically implementing the following steps:

[0097] The sum of the first weighting coefficient, the second weighting coefficient, and the third weighting coefficient is 1, wherein the first weighting coefficient is greater than 60%, the second weighting coefficient is greater than 15% and less than 25%, and the third weighting coefficient is greater than 5% and less than 15%.

[0098] In some specific embodiments, the processor, by executing a computer program stored in the memory, may further include the following steps:

[0099] Before determining the concentration of the target analyte using the concentration prediction formula and the current characteristic value, the method further includes:

[0100] Determine the concentration of historical analytes in each historical blood sample, and obtain the historical current characteristic value of each historical analyte concentration;

[0101] A concentration prediction formula is derived by fitting the historical current characteristic values ​​and the historical analyte concentrations.

[0102] In this embodiment, the power supply 23 is used to provide operating voltage for various hardware devices on the electronic device; the communication interface 24 can create a data transmission channel between the electronic device and external devices, and the communication protocol it follows can be any communication protocol applicable to the technical solution of this application, and is not specifically limited here; the input / output interface 25 is used to acquire external input data or output data to the outside world, and its specific interface type can be selected according to specific application needs, and is not specifically limited here.

[0103] The processor 21 may include one or more processing cores, such as a quad-core processor or an octa-core processor. The processor 21 may be implemented using at least one hardware form selected from DSP (Digital Signal Processing), FPGA (Field-Programmable Gate Array), and PLA (Programmable Logic Array). The processor 21 may also include a main processor and a coprocessor. The main processor, also known as a CPU (Central Processing Unit), is used to process data in the wake-up state; the coprocessor is a low-power processor used to process data in the standby state. In some embodiments, the processor 21 may integrate a GPU (Graphics Processing Unit), which is responsible for rendering and drawing the content to be displayed on the screen. In some embodiments, the processor 21 may also include an AI (Artificial Intelligence) processor, which is used to handle computational operations related to machine learning.

[0104] In addition, the memory 22, as a carrier for resource storage, can be a read-only memory, random access memory, disk or optical disk, etc. The resources stored on it include operating system 221, computer program 222 and data 223, etc., and the storage method can be temporary storage or permanent storage.

[0105] The operating system 221 manages and controls the various hardware devices and computer programs 222 on the electronic device to enable the processor 21 to perform calculations and processing on the massive amounts of data 223 in the memory 22. The operating system can be Windows, Unix, Linux, etc. The computer program 222, in addition to including a computer program capable of performing the electrochemical blood detection method disclosed in any of the foregoing embodiments, may further include computer programs capable of performing other specific tasks. The data 223 may include data received by the electronic device from external devices, as well as data collected by its own input / output interface 25.

[0106] Furthermore, this application also discloses a computer-readable storage medium for storing a computer program; wherein, when the computer program is executed by a processor, it implements the aforementioned disclosed electrochemical detection method for blood. Specific steps of this method can be found in the corresponding content disclosed in the foregoing embodiments, and will not be repeated here.

[0107] The various embodiments in this specification are described in a progressive manner, with each embodiment focusing on its differences from other embodiments. Similar or identical parts between embodiments can be referred to interchangeably. For the apparatus disclosed in the embodiments, since it corresponds to the method disclosed in the embodiments, the description is relatively simple; relevant parts can be referred to in the method section.

[0108] Those skilled in the art will further recognize that the units and algorithm steps of the various examples described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, computer software, or a combination of both. To clearly illustrate the interchangeability of hardware and software, the components and steps of the various examples have been generally described in terms of functionality in the foregoing description. Whether these functions are implemented in hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of this application. The steps of the methods or algorithms described in conjunction with the embodiments disclosed herein can be implemented directly in hardware, software modules executed by a processor, or a combination of both. The software module may be located in random access memory (RAM), memory, read-only memory (ROM), electrically programmable EPROM (EPROM), electrically erasable programmable read-only memory (EEPROM), register, hard disk, removable disk, CD-ROM (CoMP23042875act Disc Read-Only Memory), or any other form of storage medium known in the art.

[0109] Finally, it should be noted that in this document, relational terms such as "first" and "second" are used only to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or apparatus. Without further limitations, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, method, article, or apparatus that includes said element.

[0110] The above provides a detailed description of the electrochemical detection method, apparatus, equipment, and medium for blood provided by the present invention. Specific examples have been used to illustrate the principles and implementation methods of the present invention. The descriptions of the above embodiments are only for the purpose of helping to understand the method and core ideas of the present invention. At the same time, for those skilled in the art, there will be changes in the specific implementation methods and application scope based on the ideas of the present invention. Therefore, the content of this specification should not be construed as a limitation of the present invention.

Claims

1. An electrochemical detection method for blood, characterized in that, include: Based on a preset time interval, the initial current value of the target analyte in the blood sample to be tested is obtained at each time point using an electrochemical biosensor; The area of ​​the current curve is obtained using the initial current value, and target current values ​​for different preset time periods are selected from each initial current value. The target current values ​​are then weighted and summed to obtain the weighted current value. The sum of the area under the current curve and the weighted current value is determined as the current characteristic value; The concentration of the target analyte is determined using the concentration prediction formula and the current characteristic value.

2. The electrochemical detection method for blood according to claim 1, characterized in that, The electron mediator in the electrochemical biosensor includes a first electron mediator and a second electron mediator. The first electron mediator is hexaammonium trichloride ruthenium trichloride, and the second electron mediator is any one of methyl 5-methylphenazine sulfate, ethyl 5-ethylphenazine sulfate, and methyl 1-methoxy-5-methylphenazine sulfate.

3. The electrochemical detection method for blood according to claim 1, characterized in that, The step of obtaining the area under the current curve using the initial current value includes: A scatter plot is plotted using each of the initial current values ​​to obtain the current curve of the blood sample to be tested; use Calculate the area under the current curve; where A represents the area under the current curve, t represents the preset time interval, i represents the starting index of the initial current value, k represents the preset empirical value, n represents the ending index of the initial current value, and I represents the initial current value.

4. The electrochemical detection method for blood according to claim 3, characterized in that, The preset experience value ranges from 3 to 5.

5. The electrochemical detection method for blood according to claim 1, characterized in that, The step of selecting target current values ​​for different preset time periods from each of the initial current values ​​and performing a weighted summation of the target current values ​​to obtain a weighted current value includes: Select a first target current value for a first preset time period, a second target current value for a second preset time period, and a third target current value for a third preset time period from the initial current values. The first target current value, the second target current value, and the third target current value are weighted and summed using a second preset formula to obtain a weighted current value.

6. The electrochemical detection method for blood according to claim 5, characterized in that, The step of using a second preset formula to perform a weighted summation of the first target current value, the second target current value, and the third target current value to obtain a weighted current value includes: Using B = xI a +yI b +zI c The first target current value, the second target current value, and the third target current value are weighted and summed to obtain a weighted current value; where I a I represents the first target current value. b I represents the second target current value. c Let x represent the first target current value, y represent the second target current value, z represent the third target current value, and B represent the weighted current value.

7. The electrochemical detection method for blood according to claim 5, characterized in that, The first preset time period is the early stage of the acquisition cycle of the initial current value, the second preset time period is the middle stage of the acquisition cycle, and the third preset time period is the late stage of the acquisition cycle.

8. The electrochemical detection method for blood according to claim 6, characterized in that, The sum of the first weighting coefficient, the second weighting coefficient, and the third weighting coefficient is 1, wherein the first weighting coefficient is greater than 60%, the second weighting coefficient is greater than 15% and less than 25%, and the third weighting coefficient is greater than 5% and less than 15%.

9. The electrochemical detection method for blood according to any one of claims 1 to 8, characterized in that, Before determining the concentration of the target analyte using the concentration prediction formula and the current characteristic value, the method further includes: Determine the concentration of historical analytes in each historical blood sample, and obtain the historical current characteristic value of each historical analyte concentration; A concentration prediction formula is derived by fitting the historical current characteristic values ​​and the historical analyte concentrations.

10. An electrochemical detection device for blood, characterized in that, include: The first current acquisition module is used to acquire the initial current value of the target analyte in the blood sample to be tested at each time point based on a preset time interval and using an electrochemical biosensor. The second current acquisition module is used to acquire the area value of the current curve using the initial current value, and to filter out target current values ​​for different preset time periods from each initial current value, and to perform a weighted summation on each target current value to obtain a weighted current value. The feature value acquisition module is used to determine the sum of the current curve area value and the weighted current value as the current feature value; The concentration result prediction module is used to determine the concentration result of the target analyte using the concentration prediction formula and the current characteristic value.

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