A method for identifying a single-impedance channel full-hole plugging, a storage medium and an equipment

Abstract

The embodiment of the application discloses a kind of single impedance passage whole course hole identification method, storage medium and equipment, comprising: establishing the first functional relationship of white blood cell impedance passage voltage and diluent background voltage and the second functional relationship of red blood cell impedance passage voltage and diluent background voltage;After obtaining target white blood cell impedance passage voltage, when the absolute value of the first difference between current white blood cell impedance passage voltage and target white blood cell impedance passage voltage is greater than or equal to first preset threshold, it is indicated that single impedance passage occurs whole course hole when white blood cell passes through single impedance passage;After obtaining target red blood cell impedance passage voltage, when the absolute value of the second difference between current red blood cell impedance passage voltage and target red blood cell impedance passage voltage is greater than or equal to second preset threshold, it is indicated that single impedance passage occurs whole course hole when red blood cell and platelet pass through single impedance passage.The method realizes the identification of single impedance passage whole course hole, etc.

Description

Technical Field

[0001] This invention relates to the field of identification technology, and in particular to an identification method, storage medium, and device for a single impedance channel with full-length blocked vias. Background Technology

[0002] When detecting microparticles using impedance spectroscopy, an impedance channel (i.e., a small orifice or a gemstone aperture) is immersed in an electrolyte solution. A constant current power supply is applied across the impedance channel. When a microparticle passes through the impedance channel, the voltage across the channel changes; the larger the microparticle, the greater the voltage change. Since cells are also a type of microparticle, blood can be diluted and mixed in a diluent based on the above principle. Then, the change in voltage across the impedance channel can be used to count cells. The diluent is a reagent with conductivity and physiological saline properties. However, when using impedance spectroscopy to detect cells, the impedance channel is a component prone to blockage. For example, debris from the puncture tube or aggregates of large protein molecules in the blood may adhere to the inner wall of the impedance channel, causing complete blockage and preventing cell counting. Therefore, it is necessary to identify whether the impedance channel is completely blocked.

[0003] In existing technologies, when identifying whether a full-length impedance channel is blocked, it is generally done by identifying whether a dual impedance channel is blocked. This is because analyzers typically have two impedance channels: a red blood cell impedance channel and a white blood cell impedance channel, to detect red blood cells and white blood cells respectively. For cost considerations, some analyzers are configured to share a single impedance channel for red blood cells and white blood cells. However, sharing a single impedance channel increases the probability of full-length blockage. Therefore, the dual-impedance channel full-length blockage identification method is no longer applicable to the identification of single-impedance channel full-length blockage. Summary of the Invention

[0004] Based on this, it is necessary to propose a method, device, storage medium and equipment for identifying full-length via blockage of a single impedance channel to address the above problems. This enables the identification of full-length via blockage of a single impedance channel and can accurately identify whether full-length via blockage has occurred in a single impedance channel.

[0005] To achieve the above objectives, the present invention provides, in a first aspect, a method for identifying a single-impedance channel with a completely blocked via, the method comprising:

[0006] Establish the first functional relationship between leukocyte impedance channel voltage and diluent background voltage, and establish the second functional relationship between erythrocyte impedance channel voltage and diluent background voltage;

[0007] Obtain the current background voltage of the diluent and the current voltage of the leukocyte impedance channel;

[0008] The target leukocyte impedance channel voltage is obtained based on the current background voltage of the diluent and the first functional relationship, and the absolute value of the first difference between the current leukocyte impedance channel voltage and the target leukocyte impedance channel voltage is determined.

[0009] If the absolute value of the first difference is greater than or equal to the first preset threshold, then output the first full-length blockage information to indicate that the single impedance channel is completely blocked when white blood cells pass through the single impedance channel.

[0010] Obtain the current background voltage of the diluent and the current erythrocyte impedance channel voltage;

[0011] The target red blood cell impedance channel voltage is obtained based on the current red blood cell background voltage and the second functional relationship, and the absolute value of the second difference between the current red blood cell impedance channel voltage and the target red blood cell impedance channel voltage is determined.

[0012] If the absolute value of the second difference is greater than or equal to the second preset threshold, then the second full-path blockage information is output to indicate that the single impedance channel is blocked throughout when red blood cells and platelets pass through it.

[0013] Optionally, establishing the first functional relationship between the leukocyte impedance channel voltage and the diluent background voltage, and establishing the first functional relationship between the erythrocyte impedance channel voltage and the diluent background voltage, includes:

[0014] The background voltage of the dilution solution and the impedance channel voltage of leukocytes were obtained at different temperatures;

[0015] The first functional relationship was established based on the background voltage of the dilution solution and the impedance channel voltage of leukocytes at different temperatures;

[0016] The background voltage of the dilution solution and the impedance channel voltage of erythrocytes were obtained at different temperatures;

[0017] The second functional relationship was established based on the background voltage of the diluent and the impedance channel voltage of erythrocytes at different temperatures.

[0018] Optionally, establishing the first functional relationship based on the background voltage of the diluent and the leukocyte impedance channel voltage at different temperatures, and establishing the second functional relationship based on the background voltage of the diluent and the erythrocyte impedance channel voltage at different temperatures, includes:

[0019] A polynomial fitting method was used to establish the first functional relationship based on the background voltage of the diluent and the impedance channel voltage of leukocytes at different temperatures, and a second functional relationship based on the background voltage of the diluent and the impedance channel voltage of erythrocytes at different temperatures.

[0020] Optionally, the base voltage of the diluent at different temperatures is obtained by the following method:

[0021] At each temperature, the diluent is injected into the blood cell analysis pool, and the optical generation module emits a laser through the blood cell analysis pool. The laser passing through the blood cell analysis pool is received by the optical receiving module, and the background voltage of the diluent converted by the optical receiving module based on the laser passing through the blood cell analysis pool is collected to obtain the background voltage of the diluent at different temperatures.

[0022] Optionally, the leukocyte impedance channel voltage and erythrocyte impedance channel voltage at different temperatures are obtained by the following method:

[0023] At each temperature, a blood sample is perfused into a hematology analyzer and mixed with the diluent to obtain a blood diluent. A portion of the blood diluent is aspirated from the hematology analyzer, and the remaining blood diluent is hemolyzed to obtain a leukocyte diluent. The leukocyte impedance channel voltage is measured using electrodes in the hematology analyzer. After emptying and cleaning the hematology analyzer, the aspirated blood diluent and diluent are perfused into the hematology analyzer and mixed to obtain a erythrocyte diluent. The erythrocyte impedance channel voltage is measured using electrodes in the hematology analyzer to obtain the leukocyte impedance channel voltage and erythrocyte impedance channel voltage at different temperatures.

[0024] Optionally, the current base voltage of the diluent is obtained in the following way:

[0025] At the current temperature, the diluent is poured into the blood cell analysis pool. The optical generation module emits a laser through the blood cell analysis pool. The laser passing through the blood cell analysis pool is received by the optical receiving module. The background voltage of the current diluent is collected by the optical receiving module based on the laser passing through the blood cell analysis pool.

[0026] Optionally, the current leukocyte impedance channel voltage and the current erythrocyte impedance channel voltage are obtained in the following manner:

[0027] At the current temperature, a blood sample is perfused into a hematology analyzer and mixed with the diluent to obtain a blood diluent. A portion of the blood diluent is aspirated from the hematology analyzer, and the remaining blood diluent is hemolyzed to obtain a leukocyte diluent. The current leukocyte impedance channel voltage is measured using electrodes in the hematology analyzer. After emptying and cleaning the hematology analyzer, the aspirated blood diluent and diluent are perfused into the hematology analyzer and mixed to obtain a erythrocyte diluent. The current erythrocyte impedance channel voltage is measured using electrodes in the hematology analyzer.

[0028] To achieve the above objectives, the present invention provides a method for identifying a single-impedance channel with a completely blocked via in a second aspect, the method comprising:

[0029] Establish a first function curve of leukocyte impedance channel voltage versus diluent background voltage in a first rectangular coordinate system, and establish a second function curve of erythrocyte impedance channel voltage versus diluent background voltage in a second rectangular coordinate system;

[0030] Obtain the current background voltage of the diluent and the current voltage of the leukocyte impedance channel;

[0031] Determine the first function point in the first rectangular coordinate system between the current background voltage of the diluent and the current leukocyte impedance channel voltage, and calculate the first straight-line distance between the first function point and the first function curve;

[0032] If the first straight-line distance is greater than or equal to the third preset threshold, and the first function point is located above the first function curve, then output the first full-length occlusion information to represent the full-length occlusion of the single impedance channel when white blood cells pass through the single impedance channel.

[0033] Obtain the current background voltage of the diluent and the current voltage of the erythrocyte impedance channel;

[0034] Determine the second function point in the second rectangular coordinate system between the current red blood cell background voltage and the current red blood cell impedance channel voltage, and calculate the second straight-line distance between the second function point and the second function curve;

[0035] If the second straight-line distance is greater than or equal to the fourth preset threshold, and the second function point is located above the second function curve, then the second full-length blockage information is output to represent the full-length blockage of the single impedance channel when red blood cells and platelets pass through the single impedance channel.

[0036] To achieve the above objectives, the present invention provides, in a third aspect, a computer-readable storage medium storing a computer program that, when executed by a processor, causes the processor to perform the steps of the method as described in either the first or second aspect.

[0037] To achieve the above objectives, the present invention provides a computer device in a fourth aspect, including a memory and a processor, the memory storing a computer program that, when executed by the processor, causes the processor to perform the steps of the method as described in either the first or second aspect.

[0038] The present invention provides the following advantages: The method establishes a first functional relationship between the leukocyte impedance channel voltage and the diluent background voltage, and a second functional relationship between the erythrocyte impedance channel voltage and the diluent background voltage. By acquiring the current diluent background voltage and the current leukocyte impedance channel voltage, the target leukocyte impedance channel voltage is obtained based on the current diluent background voltage and the first functional relationship. Then, based on the absolute value of the first difference between the current leukocyte impedance channel voltage and the target leukocyte impedance channel voltage and the result of a first preset threshold, it is determined whether the single impedance channel experiences complete blockage when leukocytes pass through it. When the absolute value of the first difference is greater than or equal to the first preset threshold, a first complete blockage is output to indicate that the single impedance channel is completely blocked when leukocytes pass through it. The information indicates that a single impedance channel experienced complete blockage when leukocytes passed through it. It describes a method that obtains the current diluent background voltage and the current erythrocyte impedance channel voltage, calculates the target erythrocyte impedance channel voltage based on the current diluent background voltage and a second function relationship, and then determines whether complete blockage occurred when erythrocytes and platelets passed through the single impedance channel based on the absolute value of the second difference between the current and target erythrocyte impedance channel voltages and a second preset threshold. When the absolute value of the second difference is greater than or equal to the second preset threshold, it outputs second impedance channel blockage information indicating complete blockage of the single impedance channel when erythrocytes and platelets passed through it, thus confirming that complete blockage occurred. This method achieves accurate identification of complete blockage in single impedance channels. Attached Figure Description

[0039] To more clearly illustrate the technical solutions in the embodiments of the present invention 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 some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0040] in:

[0041] Figure 1 This is a schematic diagram of impedance method for cell detection in an embodiment of this application;

[0042] Figure 2 This is a flowchart illustrating a method for identifying a single-impedance channel with full-length blocked vias in an embodiment of this application.

[0043] Figure 3 This is a schematic diagram of the background voltage of the dilution solution, the red blood cell impedance channel voltage, and the white blood cell impedance channel voltage at seven different temperatures in the embodiments of this application;

[0044] Figure 4 This is another flowchart illustrating a method for identifying a single-impedance channel with full-length blocked vias in an embodiment of this application.

[0045] Figure 5 This is a schematic diagram of the first function curve of leukocyte impedance channel voltage versus diluent background voltage at seven temperatures in the first rectangular coordinate system of the embodiments of this application;

[0046] Figure 6 This is a schematic diagram of the second function curves of red blood cell impedance channel voltage versus diluent background voltage at seven temperatures in the second rectangular coordinate system of this application embodiment;

[0047] Figure 7 This is a schematic diagram of a single impedance channel being completely blocked when a white blood cell passes through it in the first rectangular coordinate system, according to an embodiment of this application.

[0048] Figure 8 This is a schematic diagram illustrating the complete blockage of the single impedance channel when red blood cells and platelets pass through it in the second rectangular coordinate system according to an embodiment of this application.

[0049] Figure 9 This is a diagram showing the internal structure of a computer device in some embodiments. Detailed Implementation

[0050] The technical solutions of the embodiments of the present invention 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 skilled in the art without creative effort are within the scope of protection of the present invention.

[0051] In the embodiments of this application, the identification of complete blockage of a single impedance channel is generally used for analyzers with a single impedance channel (if an analyzer with a dual impedance channel is used, it is also applicable if only one impedance channel is used, or if an analyzer with a dual impedance channel is used, it is also applicable if both impedance channels are used). When using an analyzer to count cells, it is used to identify whether the impedance channel (i.e., the orifice or the gemstone hole) in the analyzer is completely blocked.

[0052] Taking a hematology analyzer as an example, when counting white blood cells, red blood cells, and platelets, the analyzer generally processes the samples in the following ways to obtain white blood cell diluent (for counting white blood cells) and red blood cell diluent (for counting red blood cells and platelets): The collected blood sample and diluent are poured into the hematology analyzer's analysis chamber and mixed to obtain a blood diluent; a portion of the blood diluent is aspirated from the analysis chamber, and the remaining blood diluent is hemolyzed to obtain a white blood cell diluent; after emptying and cleaning the analysis chamber, the aspirated blood diluent and diluent are poured into the analysis chamber and mixed to obtain a red blood cell diluent; [The process is repeated here, so the translation ends here.] The purpose of hemolysis in leukocyte diluent is to dissolve red blood cells and platelets in the blood sample, leaving only white blood cells in the leukocyte diluent. The purpose of emptying and cleaning the blood cell analysis pool is to avoid the influence of the leukocyte diluent on the erythrocyte diluent. The resulting erythrocyte diluent is not hemolyzed to dissolve white blood cells in the blood sample, leaving only red blood cells and platelets. This is because white blood cells are two to three orders of magnitude smaller than red blood cells and platelets—that is, red blood cells and platelets are thousands of times larger than white blood cells—and the dilution factor of the leukocyte diluent is much smaller than that of the erythrocyte diluent. Therefore, the white blood cells in the erythrocyte diluent can be ignored.

[0053] Please see Figure 1 The diagram below illustrates the impedance method for cell detection in this embodiment. Cell dilution reagent is infused into the cell analysis chamber. Under constant negative pressure, when cells pass through the impedance channel associated with the cell analysis chamber, the impedance channel voltage changes. The impedance channel voltage can be measured by electrodes in the cell analysis chamber to count the cells.

[0054] In this embodiment, the method for identifying full-path blockage in a single-impedance channel is applied to a hematology analyzer with a single-impedance channel. This analyzer has a cell analysis pool, or hematology analysis pool. Therefore, after hemolyzing the remaining blood diluent in the hematology analysis pool to obtain a leukocyte diluent, under constant negative pressure, when leukocytes pass through the associated single-impedance channel of the hematology analysis pool, the voltage of the single-impedance channel changes. This voltage can be measured using electrodes in the hematology analysis pool when leukocytes pass through the single-impedance channel. Impedance channel voltage is used to count white blood cells. After the blood cell analysis pool is emptied and cleaned, the aspirated blood diluent and diluent are poured into the blood cell analysis pool and mixed to obtain red blood cell diluent. Under constant negative pressure, when red blood cells and platelets pass through the single impedance channel associated with the blood cell analysis pool, the single impedance channel voltage changes. That is, the voltage of the single impedance channel when red blood cells and platelets pass through the single impedance channel can be measured by electrodes in the blood cell analysis pool, i.e., the red blood cell impedance channel voltage, so as to count red blood cells and platelets.

[0055] If puncture debris or large protein molecules adhere to the single impedance channel associated with the blood cell analysis pool during the measurement phase of white blood cells, or when red blood cells and platelets pass through the same channel, this will cause the single impedance channel to experience impedance throughout the measurement, resulting in an error in the single impedance channel voltage data and preventing cell counting in that measurement. If puncture debris or large protein molecules adhere to the single impedance channel at the end of the measurement, this will also cause impedance throughout the measurement, but will result in an error in the single impedance channel voltage data for the next measurement, preventing cell counting in the next measurement.

[0056] To accurately determine whether a single impedance channel experiences complete blockage when white blood cells pass through the single impedance channel associated with the blood cell analysis pool, as well as when red blood cells and platelets pass through the single impedance channel associated with the blood cell analysis pool, a method for identifying complete blockage of a single impedance channel will be used in the following embodiments to accurately determine whether a complete blockage of a single impedance channel has occurred.

[0057] Please see Figure 2 This application provides a method for identifying a single-impedance channel with full-length blocked vias. The method includes:

[0058] Step 210: Establish the first functional relationship between the leukocyte impedance channel voltage and the background voltage of the diluent, and establish the second functional relationship between the erythrocyte impedance channel voltage and the background voltage of the diluent.

[0059] In some embodiments, the measurement of the diluent background voltage can be achieved by filling the blood cell analysis pool with the diluent, emitting a laser through the blood cell analysis pool and the diluent, and using a sensor to convert the laser light passing through the blood cell analysis pool and the diluent into a voltage, which is the diluent background voltage.

[0060] It should be noted that the conductivity of the diluent varies at different temperatures. This means that the ambient temperature can affect the accuracy of the obtained leukocyte impedance channel voltage, diluent background voltage, and erythrocyte impedance channel voltage. Therefore, to eliminate the influence of ambient temperature on the established first and second functional relationships, in some embodiments, a first functional relationship between the leukocyte impedance channel voltage and the diluent background voltage can be established based on the leukocyte impedance channel voltage and the diluent background voltage at different temperatures, and a second functional relationship can be established based on the erythrocyte impedance channel voltage and the diluent background voltage at different temperatures. In other embodiments, different environmental conditions can be used to establish the first and second functional relationships. It is understood that for those skilled in the art, using different temperatures is only a preferred option; therefore, other solutions can be adopted by changing the environmental conditions.

[0061] It should be further clarified that the different temperatures mentioned here refer to the temperatures of the leukocyte dilution reagent, diluent, and erythrocyte dilution reagent. This encompasses the various ambient temperatures that may be encountered when measuring the leukocyte impedance channel voltage of the leukocyte dilution reagent, the diluent, and the erythrocyte impedance channel voltage of the erythrocyte dilution reagent. By measuring the leukocyte impedance channel voltage, diluent background voltage, and erythrocyte impedance channel voltage at various ambient temperatures, the leukocyte impedance channel voltage, diluent background voltage, and erythrocyte impedance channel voltage at different temperatures can be obtained, thereby establishing the leukocyte impedance channel voltage W. n With the base voltage H of the diluent n The first functional relation W n =f(H n ), and establish the red blood cell impedance channel voltage R n With the base voltage H of the diluent n The second functional relationship R n =f(H n ), where n represents temperature. It can be understood that each temperature has a corresponding white blood cell impedance channel voltage, diluent background voltage, and red blood cell impedance channel voltage.

[0062] It should be noted that the process of establishing the first functional relationship between the leukocyte impedance channel voltage and the diluent background voltage in step 210, and the process of establishing the second functional relationship between the erythrocyte impedance channel voltage and the diluent background voltage, are both preset steps. After the first and second functional relationships are established for the first time, it is not necessary to repeat the establishment of the first and second functional relationships when identifying the single impedance channel full-process blockage.

[0063] Step 220: Obtain the current background voltage of the diluent and the current voltage of the leukocyte impedance channel.

[0064] In some embodiments, the acquisition of the current diluent background voltage and the current leukocyte impedance channel voltage, i.e., the acquisition under the current environmental conditions, involves obtaining the current diluent background voltage and the current leukocyte impedance channel voltage at the current temperature if the first and second functional relationships are established using temperature.

[0065] Furthermore, the current temperature refers to the current temperature of the diluent and the leukocyte diluent reagent. It can be understood that the temperature of the diluent and the leukocyte diluent reagent is equal at the current temperature. The diluent background voltage and the leukocyte impedance channel voltage of the leukocyte diluent reagent measured at the current temperature are the current diluent background voltage and the current leukocyte impedance channel voltage.

[0066] Step 230: Obtain the target leukocyte impedance channel voltage based on the current diluent background voltage and the first functional relationship, and determine the absolute value of the first difference between the current leukocyte impedance channel voltage and the target leukocyte impedance channel voltage.

[0067] In some embodiments, after obtaining the current diluent background voltage H 当前温度 Then, the current background voltage H of the diluent is... 当前温度 Substituting W into the first functional relationship between the leukocyte impedance channel voltage and the background voltage of the diluent... n =f(H n In this process, the target leukocyte impedance channel voltage W can be obtained, and the current leukocyte impedance channel voltage W can be obtained. 当前温度 After obtaining the target leukocyte impedance channel voltage W, the current leukocyte impedance channel voltage W can be calculated. 当前温度 The absolute value of the first difference between the impedance channel voltage W of the target leukocyte and the target leukocyte is ΔW = W. 当前温度 -W is used to determine whether the single impedance channel is completely blocked when white blood cells pass through it, based on the value of ΔW.

[0068] Step 240: If the absolute value of the first difference is greater than or equal to the first preset threshold, output the first full-path blockage information to represent the full-path blockage of the single impedance channel when white blood cells pass through the single impedance channel.

[0069] The first preset threshold is obtained by the operator based on historical data analysis or a large number of experiments. It can be set by the operator according to actual needs. It can be understood that the first preset threshold is the maximum allowable fluctuation range of the measured leukocyte impedance channel voltage. That is, within the maximum allowable fluctuation range of the leukocyte impedance channel voltage, a single impedance channel will not produce full-process blockage.

[0070] In some embodiments, the output of first full-length blockage information indicating that the single impedance channel is completely blocked when the leukocyte passes through it can be displayed on a screen or given a voice prompt through a speaker. It is understood that the purpose of outputting first full-length blockage information indicating that the single impedance channel is completely blocked when the leukocyte passes through it is to prompt the operator that the single impedance channel was completely blocked when the leukocyte passed through it.

[0071] Step 250: Obtain the current background voltage of the diluent and the current erythrocyte impedance channel voltage.

[0072] In some embodiments, the acquisition of the current diluent background voltage and the current erythrocyte impedance channel voltage, i.e., the acquisition under the current environmental conditions, involves obtaining the current diluent background voltage and the current erythrocyte impedance channel voltage at the current temperature if the first and second functional relationships are established using temperature.

[0073] Furthermore, the current temperature (i.e., the temperature mentioned in step 220, where the current diluent background voltage is the same as the current diluent background voltage in step 220) refers to the current temperature of the diluent and the red blood cell diluent reagent. It can be understood that the temperatures of the diluent and the red blood cell diluent reagent are equal at the current temperature. The diluent background voltage of the diluent and the red blood cell impedance channel voltage of the red blood cell diluent measured at the current temperature are the current diluent background voltage and the current red blood cell impedance channel voltage.

[0074] Step 260: Obtain the target red blood cell impedance channel voltage based on the current red blood cell background voltage and the second function relationship, and determine the absolute value of the second difference between the current red blood cell impedance channel voltage and the target red blood cell impedance channel voltage.

[0075] In some embodiments, after obtaining the current diluent background voltage H 当前温度 Then, the current background voltage H of the diluent is... 当前温度 Substituting the second function relationship between the erythrocyte impedance channel voltage and the background voltage of the diluent, R... n =f(H n In this process, the target red blood cell impedance channel voltage R can be obtained, and the current red blood cell impedance channel voltage R can be obtained.当前温度 After obtaining the target erythrocyte impedance channel voltage R, the current erythrocyte impedance channel voltage R can be calculated. 当前温度 The absolute value of the second difference between the target red blood cell impedance channel voltage R and the target red blood cell impedance channel voltage R is ΔR = R 当前温度 -R is used to determine whether the single impedance channel is completely blocked when red blood cells and platelets pass through it, based on the value of ΔR.

[0076] Step 270: If the absolute value of the second difference is greater than or equal to the second preset threshold, then output the second full-path blockage information to represent the full-path blockage of the single impedance channel when red blood cells and platelets pass through the single impedance channel.

[0077] The second preset threshold is obtained by the operator based on historical data analysis or a large number of experiments. It can be set by the operator according to actual needs. It can be understood that the second preset threshold is the maximum allowable fluctuation range of the measured red blood cell impedance channel voltage. That is, within the maximum allowable fluctuation range of the red blood cell impedance channel voltage, a single impedance channel will not produce full-process blockage.

[0078] In some embodiments, the output of second full-path blockage information indicating that the single impedance channel is completely blocked when red blood cells and platelets pass through it can be displayed on a screen or given a voice prompt through a speaker. It is understood that the purpose of outputting second full-path blockage information indicating that the single impedance channel is completely blocked when red blood cells and platelets pass through it is to prompt the operator that the single impedance channel is completely blocked when the red blood cells and platelets pass through it.

[0079] In this embodiment, a first functional relationship is established between the leukocyte impedance channel voltage and the diluent background voltage, and a second functional relationship is established between the erythrocyte impedance channel voltage and the diluent background voltage. The current diluent background voltage and the current leukocyte impedance channel voltage are obtained. The target leukocyte impedance channel voltage is obtained based on the current diluent background voltage and the first functional relationship. Then, based on the absolute value of the first difference between the current leukocyte impedance channel voltage and the target leukocyte impedance channel voltage and the result of a first preset threshold, it is determined whether the single impedance channel experiences complete blockage when leukocytes pass through it. When the absolute value of the first difference is greater than or equal to the first preset threshold, first complete blockage information indicating complete blockage of the single impedance channel when leukocytes pass through it is output. When leukocytes pass through a single impedance channel, the single impedance channel experiences complete blockage. This method identifies whether complete blockage occurs when leukocytes and platelets pass through the single impedance channel by acquiring the current diluent background voltage and the current erythrocyte impedance channel voltage, and then calculates the target erythrocyte impedance channel voltage based on the relationship between the current diluent background voltage and the second function. Finally, it determines whether complete blockage occurs when erythrocytes and platelets pass through the single impedance channel by comparing the absolute value of the second difference between the current and target erythrocyte impedance channel voltages with a second preset threshold. When the absolute value of the second difference is greater than or equal to the second preset threshold, it outputs second impedance channel blockage information, indicating that complete blockage has occurred when erythrocytes and platelets pass through the single impedance channel. This method achieves accurate identification of complete blockage in single impedance channels.

[0080] In one feasible implementation, step 210 establishes a first functional relationship between the leukocyte impedance channel voltage and the diluent background voltage, and establishes a first functional relationship between the erythrocyte impedance channel voltage and the diluent background voltage, including: obtaining the diluent background voltage and leukocyte impedance channel voltage at different temperatures; establishing a first functional relationship based on the diluent background voltage and leukocyte impedance channel voltage at different temperatures; obtaining the diluent background voltage and erythrocyte impedance channel voltage at different temperatures; and establishing a second functional relationship based on the diluent background voltage and erythrocyte impedance channel voltage at different temperatures.

[0081] It is understandable that there is a corresponding leukocyte impedance channel voltage, diluent background voltage, and erythrocyte impedance channel voltage at each temperature, so as to establish a first functional relationship and a second functional relationship based on multiple corresponding leukocyte impedance channel voltages, diluent background voltages, and erythrocyte impedance channel voltages.

[0082] In this embodiment of the application, by preferably establishing a first functional relationship based on the base voltage of the diluent and the voltage of the leukocyte impedance channel at different temperatures, and establishing a second functional relationship based on the base voltage of the diluent and the voltage of the erythrocyte impedance channel at different temperatures, the influence of temperature on the voltage of the single impedance channel can be eliminated, so that it is possible to accurately identify whether the single impedance channel has been completely blocked.

[0083] In one feasible implementation, the base voltage of the diluent at different temperatures in the above embodiments is obtained by the following method: at each temperature, the diluent is injected into the blood cell analysis pool, the optical generation module emits a laser through the blood cell analysis pool, the laser passing through the blood cell analysis pool is received by the optical receiving module, and the base voltage of the diluent converted by the optical receiving module based on the laser passing through the blood cell analysis pool is collected to obtain the base voltage of the diluent at different temperatures.

[0084] In some embodiments, since the temperatures of red blood cell diluents and white blood cell diluents are generally between 10°C and 35°C, and the temperature of the diluent is also between 10°C and 35°C, the diluent background voltage can be measured using diluents at seven temperature steps: 13.4°C, 16.6°C, 22.7°C, 28.0°C, 32.9°C, 37.3°C, and 44.2°C. This yields the diluent background voltage at seven temperature steps. Specifically, at 13.4°C, the diluent is poured into the red blood cell analysis chamber, and the white blood cell diluent is poured into the white blood cell analysis chamber. The optical generation module is then controlled to emit a laser through the blood cell analyzer. The system uses an optical receiving module to receive laser light passing through a blood cell analysis cell. The optical receiving module then collects the background voltage of the diluent based on the laser light passing through the blood cell analysis cell, obtaining the background voltage of the diluent at 13.4 degrees Celsius. At 16.6 degrees Celsius, the diluent is infused into the red blood cell analysis cell, and the white blood cell diluent is infused into the white blood cell analysis cell. The optical generating module then emits laser light through the blood cell analysis cell. The optical receiving module receives the laser light passing through the blood cell analysis cell and collects the background voltage of the diluent based on the laser light passing through the blood cell analysis cell, obtaining the background voltage of the diluent at 16.6 degrees Celsius. This process is repeated until the background voltage of the diluent at seven temperature steps is obtained. For an example, please refer to [link to example]. Figure 3 This is a schematic diagram of the background voltage of the diluent, the red blood cell impedance channel voltage, and the white blood cell impedance channel voltage at seven different temperatures in the embodiments of this application.

[0085] In this embodiment, by injecting diluent into the blood cell analysis pool at each temperature, the optical generation module emits a laser through the blood cell analysis pool, and the optical receiving module receives the laser passing through the blood cell analysis pool. The optical receiving module collects the diluent background voltage converted by the laser passing through the blood cell analysis pool, thus obtaining the diluent background voltage at different temperatures. This ensures that there is a corresponding diluent background voltage at each temperature gradient, which facilitates the identification of full-path blockage of a single impedance channel by establishing a first functional relationship and a second functional relationship. This can accurately identify whether a single impedance channel is fully blocked and ensure that the voltage of the single impedance channel is independent of the temperature, thus solving the problem of false alarms of full-path blockage of the single impedance channel.

[0086] In one feasible implementation, the leukocyte impedance channel voltage and erythrocyte impedance channel voltage at different temperatures in the above embodiments are obtained as follows: at each temperature, a blood sample is perfused into a hematology analyzer and mixed with a diluent to obtain a blood diluent. A portion of the blood diluent in the hematology analyzer is aspirated as an erythrocyte diluent. The remaining blood diluent in the hematology analyzer is hemolyzed to obtain a leukocyte diluent. The leukocyte impedance channel voltage is measured using electrodes in the hematology analyzer. After emptying and cleaning the hematology analyzer, the erythrocyte diluent and diluent are perfused into the hematology analyzer and mixed. The erythrocyte impedance channel voltage is then measured using electrodes in the hematology analyzer to obtain the leukocyte impedance channel voltage and erythrocyte impedance channel voltage at different temperatures.

[0087] In some embodiments, while measuring the base voltage of the diluent using diluents at seven temperature steps (13.4°C, 16.6°C, 22.7°C, 28.0°C, 32.9°C, 37.3°C, and 44.2°C), it is also necessary to measure the leukocyte impedance channel voltage and erythrocyte impedance channel voltage using leukocyte and erythrocyte diluents at the same seven temperature steps. The impedance channel voltages of leukocytes and erythrocytes were measured at seven temperature steps. Specifically, after obtaining the base voltage of the diluent at 13.4 degrees Celsius, blood samples were perfused into the hematology analyzer and mixed with the diluent to obtain a blood diluent. A portion of the blood diluent was extracted from the hematology analyzer to obtain an erythrocyte diluent. The remaining blood diluent in the hematology analyzer was hemolyzed to obtain a leukocyte diluent. The leukocyte impedance channel voltage was then measured using electrodes in the hematology analyzer. After purging and cleaning, the erythrocyte diluent and diluent were perfused into the hematology analysis chamber and mixed. The erythrocyte impedance channel voltage was then measured using electrodes in the chamber to obtain the leukocyte impedance channel voltage and the erythrocyte impedance channel voltage at 13.4°C. The diluent background voltage at 16.6°C was then obtained. Blood samples were then perfused into the hematology analysis chamber and mixed with the diluent to obtain the blood diluent. A portion of the blood diluent was aspirated from the hematology analysis chamber as the erythrocyte diluent. The remaining blood diluent is hemolyzed to obtain a leukocyte diluent. The leukocyte impedance channel voltage is measured using electrodes in the hematology analyzer. After draining and cleaning the hematology analyzer, the erythrocyte diluent and diluent are infused into the hematology analyzer for homogenization. The erythrocyte impedance channel voltage is then measured using electrodes in the hematology analyzer to obtain the leukocyte and erythrocyte impedance channel voltages at 16.6 degrees Celsius. This process is repeated until the leukocyte and erythrocyte impedance channel voltages at seven temperature gradients are obtained. For an example, please refer to [continued]. Figure 3 .

[0088] In this embodiment, blood samples are perfused into a blood cell analysis pool at each temperature and mixed with a diluent to obtain a blood diluent. A portion of the blood diluent in the blood cell analysis pool is aspirated to obtain a red blood cell diluent. The remaining blood diluent in the blood cell analysis pool is hemolyzed to obtain a white blood cell diluent. The white blood cell impedance channel voltage is measured using electrodes in the blood cell analysis pool. After emptying and cleaning the blood cell analysis pool, the red blood cell diluent and diluent are perfused into the blood cell analysis pool and mixed. The red blood cell impedance channel voltage is then measured using electrodes in the blood cell analysis pool to obtain the white blood cell impedance channel voltage and red blood cell impedance channel voltage at different temperatures. This ensures that there is a corresponding white blood cell impedance channel voltage and red blood cell impedance channel voltage at each temperature gradient. This facilitates the establishment of a first functional relationship and a second functional relationship to identify the complete blockage of a single impedance channel. It can accurately identify whether a single impedance channel has been completely blocked and ensures that the voltage of the single impedance channel is independent of the temperature effect, thus solving the problem of false alarms about complete blockage of a single impedance channel.

[0089] In one feasible implementation, a first functional relationship is established based on the background voltage of the diluent and the impedance channel voltage of leukocytes at different temperatures, and a second functional relationship is established based on the background voltage of the diluent and the impedance channel voltage of erythrocytes at different temperatures. This includes: using a polynomial fitting method to establish the first functional relationship based on the background voltage of the diluent and the impedance channel voltage of leukocytes at different temperatures, and to establish the second functional relationship based on the background voltage of the diluent and the impedance channel voltage of erythrocytes at different temperatures.

[0090] It should be noted that polynomial fitting is a mathematical optimization algorithm, which has been described in detail in existing technologies and will not be repeated here. Essentially, polynomial fitting is the least squares method for curve fitting. The least squares method finds the optimal function match for the data by minimizing the sum of squared errors. In some embodiments, the optimal function is obtained using sample data from seven temperature gradients (leukocyte impedance channel voltage and diluent background voltage, and erythrocyte impedance channel voltage and diluent background voltage). The unknown data (i.e., the impedance channel voltage of the target white blood cells and the impedance channel voltage of the target red blood cells) are solved using the optimal function, so as to minimize the sum of squares of the errors between the solved data and the actual data.

[0091] In this embodiment, by employing a polynomial fitting method to establish a first functional relationship based on the base voltage of the diluent and the voltage of the leukocyte impedance channel at different temperatures, and to establish a second functional relationship based on the base voltage of the diluent and the voltage of the erythrocyte impedance channel at different temperatures, the sum of squares between the calculated target leukocyte impedance channel voltage and the actual current leukocyte impedance channel voltage can be minimized, as can the sum of squares between the calculated target erythrocyte impedance channel voltage and the actual current erythrocyte impedance channel voltage. This allows for accurate identification of whether a single impedance channel is completely blocked.

[0092] In one feasible implementation, in step 220, the current diluent background voltage is obtained by: at the current temperature, the diluent is injected into the blood cell analysis pool, the optical generation module emits a laser through the blood cell analysis pool, the laser passing through the blood cell analysis pool is received by the optical receiving module, and the current diluent background voltage converted by the optical receiving module based on the laser passing through the blood cell analysis pool is collected.

[0093] In this embodiment, by filling the blood cell analysis pool with diluent at the current temperature, the optical generation module emits a laser through the blood cell analysis pool, and the optical receiving module receives the laser passing through the blood cell analysis pool. The optical receiving module collects the current diluent background voltage based on the laser passing through the blood cell analysis pool. This avoids the inaccuracy of the current diluent background voltage when using the current diluent background voltage for identification of single-impedance channel full-process blockage, which would prevent the counting of cells.

[0094] In one feasible implementation, in step 220, the current leukocyte impedance channel voltage and the current erythrocyte impedance channel voltage are obtained as follows: at the current temperature, a blood sample is perfused into a hematology analyzer and mixed with a diluent to obtain a blood diluent; a portion of the blood diluent in the hematology analyzer is aspirated as an erythrocyte diluent; the remaining blood diluent in the hematology analyzer is hemolyzed to obtain a leukocyte diluent; the current leukocyte impedance channel voltage is measured using electrodes in the hematology analyzer; after emptying and cleaning the hematology analyzer, the erythrocyte diluent and diluent are perfused into the hematology analyzer and mixed; and the current erythrocyte impedance channel voltage is measured using electrodes in the hematology analyzer.

[0095] In this embodiment, a blood sample is perfused into a blood cell analysis pool at the current temperature and mixed with a diluent to obtain a blood diluent. A portion of the blood diluent in the blood cell analysis pool is aspirated to obtain a red blood cell diluent. The remaining blood diluent in the blood cell analysis pool is hemolyzed to obtain a white blood cell diluent. The current white blood cell impedance channel voltage is measured using electrodes in the blood cell analysis pool. After emptying and cleaning the blood cell analysis pool, the red blood cell diluent and diluent are perfused into the blood cell analysis pool and mixed. The current red blood cell impedance channel voltage is then measured using electrodes in the blood cell analysis pool. This avoids the inaccuracy of the current white blood cell impedance channel voltage and the current red blood cell impedance channel voltage when using them for single-impedance channel full-throughput hole blockage identification, which would prevent cell counting from being achieved.

[0096] Please see Figure 4 This is another flowchart illustrating a method for identifying a single-impedance channel with full-length blocked vias in an embodiment of this application. The method includes:

[0097] In step 410: Establish a first function curve of leukocyte impedance channel voltage versus diluent background voltage in a first rectangular coordinate system, and establish a second function curve of erythrocyte impedance channel voltage versus diluent background voltage in a second rectangular coordinate system.

[0098] It should be noted that the data on leukocyte impedance channel voltage, diluent background voltage, and erythrocyte impedance channel voltage can be obtained under different environmental conditions. In some embodiments, different temperatures are preferably used. That is, in the above embodiments, at each temperature, the diluent is perfused into the blood cell analysis pool, the optical generator module emits a laser through the blood cell analysis pool, the optical receiver module receives the laser passing through the blood cell analysis pool, and the optical receiver module collects the diluent background voltage converted by the laser passing through the blood cell analysis pool. The blood sample is then perfused into the blood cell analysis pool and mixed with the diluent to obtain the data. The blood diluent was obtained by aspirating a portion of the blood diluent from the blood cell analysis pool to obtain the erythrocyte diluent. The remaining blood diluent in the blood cell analysis pool was hemolyzed to obtain the leukocyte diluent. The leukocyte impedance channel voltage was measured using electrodes in the blood cell analysis pool. After emptying and cleaning the blood cell analysis pool, the erythrocyte diluent and diluent were poured into the blood cell analysis pool for mixing. The erythrocyte impedance channel voltage, the background voltage of the diluent, and the erythrocyte impedance channel voltage at different temperatures were then measured using electrodes in the blood cell analysis pool. These results are not described in detail here.

[0099] It should be further explained that, in some embodiments, the process of establishing the first function curve of leukocyte impedance channel voltage versus diluent background voltage in the first rectangular coordinate system and the second function curve of erythrocyte impedance channel voltage versus diluent background voltage in the second rectangular coordinate system can be achieved by using the polynomial fitting method described in the above embodiments to obtain the first function relationship. The values ​​of a1, b1, c1, and d1 in the equation, and the resulting second functional relationship. The values ​​of a2, b2, c3, and d4 are used to establish a first function curve of leukocyte impedance channel voltage versus diluent background voltage in a first rectangular coordinate system, and an erythrocyte impedance channel voltage versus diluent background voltage in a second rectangular coordinate system. In other embodiments, a scatter plot of leukocyte impedance channel voltage versus diluent background voltage can be plotted in the first rectangular coordinate system, and then the first function curve can be determined based on the distance between the scatter plots. For example, using... Figure 3 The first function curve obtained from seven temperature data points is shown below. Figure 5 This document presents a schematic diagram of the first function curves of leukocyte impedance channel voltage and diluent background voltage at seven temperatures in a first rectangular coordinate system, and a scatter plot of erythrocyte impedance channel voltage and diluent background voltage in a second rectangular coordinate system. The second function curve is then determined based on the distances between the scatter plots. For example, [the document uses...] Figure 3 The second function curve obtained from seven temperature data points is shown in the attached image. Figure 6 This is a schematic diagram of the second function curves of the red blood cell impedance channel voltage and the diluent background voltage at seven temperatures in the second rectangular coordinate system of this application embodiment.

[0100] It should also be noted that step 410 corresponds to step 210. That is, the process of establishing the first function curve of the voltage of the leukocyte impedance channel and the background voltage of the diluent, and the process of establishing the second function curve of the voltage of the erythrocyte impedance channel and the background voltage of the diluent are also preset steps. After the first function curve and the second function curve are established for the first time, it is not necessary to repeat the establishment of the first function curve and the second function curve when identifying the blockage of the single impedance channel throughout the process.

[0101] Step 420: Obtain the current diluent background voltage and the current leukocyte impedance channel voltage.

[0102] It should be noted that, for obtaining the current diluent background voltage and the current leukocyte impedance channel voltage, step 220 in the above embodiments can be used, or in the above embodiments, at the current temperature, the diluent is poured into the blood cell analysis pool, the optical generation module emits a laser through the blood cell analysis pool, the laser passing through the blood cell analysis pool is received by the optical receiving module, the current diluent background voltage converted by the optical receiving module based on the laser passing through the blood cell analysis pool is collected, the blood sample is poured into the blood cell analysis pool and mixed with the diluent to obtain blood diluent, a portion of the blood diluent in the blood cell analysis pool is aspirated as red blood cell diluent, the remaining blood diluent in the blood cell analysis pool is hemolyzed to obtain white blood cell diluent, and the current leukocyte impedance channel voltage is measured through the electrodes in the blood cell analysis pool, which will not be elaborated here.

[0103] In step 430: Determine the first function point of the current diluent background voltage and the current leukocyte impedance channel voltage in the first rectangular coordinate system, and calculate the first straight-line distance between the first function point and the first function curve.

[0104] In some embodiments, the current diluent background voltage H is obtained. 当前温度 and the current leukocyte impedance channel voltage W 当前温度 Then, the first function point (H) can be determined based on the distance between the X-axis and Y-axis in the first rectangular coordinate system. 当前温度 W 当前温度 After obtaining the first function point, the distance between the first function point and the first straight line of the first function curve can be calculated using the distance formula from the point to the curve.

[0105] In step 440: If the first straight-line distance is greater than or equal to the third preset threshold, and the first function point is located above the first function curve, then output the first full-length pore-blocking information to represent the full-length pore blockage of the single impedance channel when white blood cells pass through the single impedance channel.

[0106] The third preset threshold is obtained by the operator based on historical data analysis or a large number of experiments. It can be set by the operator according to actual needs. It can be understood that the third preset threshold is the maximum allowable fluctuation range of the measured leukocyte impedance channel voltage. That is, within the maximum allowable fluctuation range of the leukocyte impedance channel voltage, a single impedance channel will not produce full-process blockage.

[0107] In some embodiments, the output of first full-length blockage information indicating that the single impedance channel is completely blocked when the leukocyte passes through it can be displayed on a screen or given a voice prompt through a speaker. It is understood that the purpose of outputting first full-length blockage information indicating that the single impedance channel is completely blocked when the leukocyte passes through it is to prompt the operator that the single impedance channel was completely blocked when the leukocyte passed through it.

[0108] In some embodiments, for example, see Figure 7 This is a schematic diagram of the single impedance channel being completely blocked when leukocytes pass through the single impedance channel in the first rectangular coordinate system according to an embodiment of this application.

[0109] Step 450: Obtain the current background voltage of the diluent and the current erythrocyte impedance channel voltage.

[0110] It should be noted that, to obtain the current diluent background voltage and the current erythrocyte impedance channel voltage, step 450 in the above embodiments can be used, or in the above embodiments, after obtaining the current diluent background voltage and the current leukocyte impedance channel voltage at the current temperature, the blood cell analysis pool is emptied and cleaned, and then the erythrocyte diluent and diluent are poured into the blood cell analysis pool for mixing. The current erythrocyte impedance channel voltage is then measured through the electrodes in the blood cell analysis pool. This will not be elaborated further here.

[0111] Step 460: Determine the second function point of the current red blood cell background voltage and the current red blood cell impedance channel voltage in the second rectangular coordinate system, and calculate the second straight line distance between the second function point and the second function curve.

[0112] In some embodiments, the current diluent background voltage H is obtained. 当前温度 and the current red blood cell impedance channel voltage R 当前温度 Then, the first function point (H) can be determined based on the distance between the X-axis and Y-axis in the first rectangular coordinate system. 当前温度 R 当前温度 After obtaining the second function point, the distance between the second function point and the second straight line of the second function curve can be calculated using the distance formula from the point to the curve.

[0113] Step 470: If the second straight line distance is greater than or equal to the fourth preset threshold, and the second function point is located above the second function curve, then output the second full-length occlusion information to represent the full-length occlusion of the single impedance channel when red blood cells and platelets pass through the single impedance channel.

[0114] The fourth preset threshold is obtained by the operator based on historical data analysis or a large number of experiments. It can be set by the operator according to actual needs. It can be understood that the fourth preset threshold is the maximum allowable fluctuation range of the measured red blood cell impedance channel voltage. That is, within the maximum allowable fluctuation range of the red blood cell impedance channel voltage, a single impedance channel will not produce full-process blockage.

[0115] In some embodiments, the output of second full-path blockage information indicating that the single impedance channel is completely blocked when red blood cells and platelets pass through it can be displayed on a screen or given a voice prompt through a speaker. It is understood that the purpose of outputting second full-path blockage information indicating that the single impedance channel is completely blocked when red blood cells and platelets pass through it is to prompt the operator that the single impedance channel is completely blocked when the red blood cells and platelets pass through it.

[0116] In some embodiments, for example, see Figure 8 This is a schematic diagram of the single impedance channel being completely blocked when red blood cells and platelets pass through the single impedance channel in the second rectangular coordinate system in an embodiment of this application.

[0117] In this embodiment, a first function curve of leukocyte impedance channel voltage versus diluent background voltage is established in a first rectangular coordinate system, and a second function curve of erythrocyte impedance channel voltage versus diluent background voltage is established in a second rectangular coordinate system. The current diluent background voltage and the current leukocyte impedance channel voltage are obtained. The target leukocyte impedance channel voltage is obtained based on the current diluent background voltage and the first function relationship. A first function point is determined in the first rectangular coordinate system between the current diluent background voltage and the current leukocyte impedance channel voltage. Based on the result of the first straight-line distance between the first function point and the first function curve and a third preset threshold, it is determined whether the single impedance channel experiences complete blockage when leukocytes pass through it. When the first straight-line distance is greater than or equal to the third preset threshold, and the first function point is located above the first function curve, a first full blockage is output to indicate that the single impedance channel is completely blocked when leukocytes pass through it. This method identifies complete blockage of a single impedance channel when leukocytes pass through it. It obtains the current diluent background voltage and the current erythrocyte impedance channel voltage, calculates the target erythrocyte impedance channel voltage based on the relationship between the current diluent background voltage and a second function, and determines the second function point in a second rectangular coordinate system between the current diluent background voltage and the current erythrocyte impedance channel voltage. Based on the distance between the second function point and the second function curve, and a fourth preset threshold, it determines whether complete blockage occurs in the single impedance channel when erythrocytes and platelets pass through it. When the second straight-line distance is greater than or equal to the fourth preset threshold, and the second function point is above the second function curve, it outputs the second impedance channel complete blockage information, indicating that complete blockage occurred in the single impedance channel when erythrocytes and platelets passed through it. This method achieves the identification of complete blockage in a single impedance channel and can accurately identify whether complete blockage has occurred.

[0118] In some embodiments, a computer-readable storage medium is provided, storing a computer program, which, when executed by a processor, causes the processor to perform a method for identifying a single-impedance channel with full-length via blockage as described in the above method embodiments.

[0119] In some embodiments, a computer device is provided, including a memory and a processor, wherein the memory stores a computer program, and when the computer program is executed by the processor, the processor performs a method for identifying a single-impedance channel full-length blocked via in the above method embodiments.

[0120] Figure 9 The diagram illustrates the internal structure of a computer device in some embodiments. This computer device may specifically be a terminal, a server, or a gateway. Figure 9As shown, the computer device includes a processor, memory, and network interface connected via a system bus.

[0121] The memory includes a non-volatile storage medium and internal memory. The non-volatile storage medium of the computer device stores an operating system and may also store a computer program. When executed by a processor, this computer program causes the processor to perform the steps in the above method embodiments. The internal memory may also store a computer program, which, when executed by a processor, causes the processor to perform the steps in the above method embodiments. Those skilled in the art will understand that... Figure 9 The structure shown is merely a block diagram of a portion of the structure related to the present application and does not constitute a limitation on the computer device to which the present application is applied. Specific computer devices may include more or fewer components than those shown in the figure, or combine certain components, or have different component arrangements.

[0122] Those skilled in the art will understand that all or part of the processes in the methods of the above embodiments can be implemented by a computer program instructing related hardware. The program can be stored in a non-volatile computer-readable storage medium, and when the program is executed, it can include the processes of the embodiments of the above methods.

[0123] Any references to memory, storage, database, or other media used in the embodiments provided in this application may include non-volatile and / or volatile memory. Non-volatile memory may include read-only memory (ROM), programmable ROM (PROM), electrically programmable ROM (EPROM), electrically erasable programmable ROM (EEPROM), or flash memory. Volatile memory may include random access memory (RAM) or external cache memory. By way of illustration and not limitation, RAM is available in various forms, such as static RAM (SRAM), dynamic RAM (DRAM), synchronous DRAM (SDRAM), dual data rate SDRAM (DDRSDRAM), enhanced SDRAM (ESDRAM), synchronous link DRAM (SLDRAM), RAMbus direct RAM (RDRAM), direct memory bus dynamic RAM (DRDRAM), and RAMbus dynamic RAM (RDRAM), etc.

[0124] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0125] The embodiments described above are merely illustrative of several implementation methods of this application, and while the descriptions are specific and detailed, they should not be construed as limiting the scope of this patent application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this patent application should be determined by the appended claims.

Claims

1. A method for identifying full-length blocked vias in a single impedance channel, characterized in that, The method includes: Establish the first functional relationship between leukocyte impedance channel voltage and diluent background voltage, and establish the second functional relationship between erythrocyte impedance channel voltage and diluent background voltage; Obtain the current background voltage of the diluent and the current voltage of the leukocyte impedance channel; The target leukocyte impedance channel voltage is obtained based on the current background voltage of the diluent and the first functional relationship, and the absolute value of the first difference between the current leukocyte impedance channel voltage and the target leukocyte impedance channel voltage is determined. If the absolute value of the first difference is greater than or equal to the first preset threshold, then output the first full-length blockage information to indicate that the single impedance channel is completely blocked when white blood cells pass through the single impedance channel. Obtain the current background voltage of the diluent and the current erythrocyte impedance channel voltage; The target erythrocyte impedance channel voltage is obtained based on the current background voltage of the diluent and the second functional relationship, and the absolute value of the second difference between the current erythrocyte impedance channel voltage and the target erythrocyte impedance channel voltage is determined. If the absolute value of the second difference is greater than or equal to the second preset threshold, then output the second full-path blockage information to indicate that the single impedance channel is blocked throughout when red blood cells and platelets pass through the single impedance channel. The establishment of a first functional relationship between the leukocyte impedance channel voltage and the diluent background voltage, and the establishment of a second functional relationship between the erythrocyte impedance channel voltage and the diluent background voltage, include: The background voltage of the dilution solution and the impedance channel voltage of leukocytes were obtained at different temperatures; The first functional relationship was established based on the background voltage of the dilution solution and the impedance channel voltage of leukocytes at different temperatures; The background voltage of the dilution solution and the impedance channel voltage of erythrocytes were obtained at different temperatures; The second functional relationship was established based on the background voltage of the diluent and the impedance channel voltage of erythrocytes at different temperatures.

2. The method according to claim 1, characterized in that, The establishment of the first functional relationship based on the background voltage of the diluent and the leukocyte impedance channel voltage at different temperatures, and the establishment of the second functional relationship based on the background voltage of the diluent and the erythrocyte impedance channel voltage at different temperatures, include: A polynomial fitting method was used to establish the first functional relationship based on the background voltage of the diluent and the impedance channel voltage of leukocytes at different temperatures, and a second functional relationship based on the background voltage of the diluent and the impedance channel voltage of erythrocytes at different temperatures.

3. The method according to claim 1, characterized in that, The base voltage of the dilution solution at different temperatures was obtained as follows: At each temperature, the diluent is injected into the blood cell analysis pool, and the optical generation module emits a laser through the blood cell analysis pool. The laser passing through the blood cell analysis pool is received by the optical receiving module, and the background voltage of the diluent converted by the optical receiving module based on the laser passing through the blood cell analysis pool is collected to obtain the background voltage of the diluent at different temperatures.

4. The method according to claim 3, characterized in that, The impedance channel voltages of leukocytes and erythrocytes at different temperatures were obtained as follows: At each temperature, a blood sample is perfused into a hematology analyzer and mixed with the diluent to obtain a blood diluent. A portion of the blood diluent is aspirated from the hematology analyzer, and the remaining blood diluent is hemolyzed to obtain a leukocyte diluent. The leukocyte impedance channel voltage is measured using electrodes in the hematology analyzer. After emptying and cleaning the hematology analyzer, the aspirated blood diluent and diluent are perfused into the hematology analyzer and mixed to obtain a erythrocyte diluent. The erythrocyte impedance channel voltage is measured using electrodes in the hematology analyzer to obtain the leukocyte impedance channel voltage and erythrocyte impedance channel voltage at different temperatures.

5. The method according to claim 1, characterized in that, The current base voltage of the diluent is obtained as follows: At the current temperature, the diluent is poured into the blood cell analysis pool. The optical generation module emits a laser through the blood cell analysis pool. The laser passing through the blood cell analysis pool is received by the optical receiving module. The background voltage of the current diluent is collected by the optical receiving module based on the laser passing through the blood cell analysis pool.

6. The method according to claim 5, characterized in that, The current white blood cell impedance channel voltage and the current red blood cell impedance channel voltage are obtained in the following manner: At the current temperature, a blood sample is perfused into a hematology analyzer and mixed with the diluent to obtain a blood diluent. A portion of the blood diluent is aspirated from the hematology analyzer, and the remaining blood diluent is hemolyzed to obtain a leukocyte diluent. The current leukocyte impedance channel voltage is measured using electrodes in the hematology analyzer. After emptying and cleaning the hematology analyzer, the aspirated blood diluent and diluent are perfused into the hematology analyzer and mixed to obtain a erythrocyte diluent. The current erythrocyte impedance channel voltage is measured using electrodes in the hematology analyzer.

7. A method for identifying full-length blocked vias in a single impedance channel, characterized in that, The method includes: Establish a first function curve of leukocyte impedance channel voltage versus diluent background voltage in a first rectangular coordinate system, and establish a second function curve of erythrocyte impedance channel voltage versus diluent background voltage in a second rectangular coordinate system; Obtain the current background voltage of the diluent and the current voltage of the leukocyte impedance channel; Determine the first function point in the first rectangular coordinate system between the current background voltage of the diluent and the current leukocyte impedance channel voltage, and calculate the first straight-line distance between the first function point and the first function curve; If the first straight-line distance is greater than or equal to the third preset threshold, and the first function point is located above the first function curve, then output the first full-length occlusion information to represent the full-length occlusion of the single impedance channel when white blood cells pass through the single impedance channel. Obtain the current background voltage of the diluent and the current voltage of the erythrocyte impedance channel; Determine the second function point in the second rectangular coordinate system between the current background voltage of the diluent and the current erythrocyte impedance channel voltage, and calculate the second straight-line distance between the second function point and the second function curve; If the second straight-line distance is greater than or equal to the fourth preset threshold, and the second function point is located above the second function curve, then the second full-length blockage information is output to represent the full-length blockage of the single impedance channel when red blood cells and platelets pass through the single impedance channel.

8. A computer-readable storage medium, characterized in that, The device stores a computer program that, when executed by a processor, causes the processor to perform the steps of the method as described in any one of claims 1 to 7.

9. A computer device, characterized in that, It includes a memory and a processor, the memory storing a computer program that, when executed by the processor, causes the processor to perform the steps of the method as described in any one of claims 1 to 7.

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