Temperature Abnormality Judgment Method and Data Calibration Method for Blood Gas Analyzer

Abstract

The present invention provides a method for judging temperature abnormality and a method for data correction of a blood gas biochemical analyzer. According to a plurality of ambient temperatures and a plurality of heating element temperatures, a plurality of ambient temperature filtering results and heating element temperature filtering results are obtained; if each heating element temperature filtering result meets the heating element threshold temperature, and the air duct temperature at the currently obtained time belongs to the air duct threshold temperature range, it is confirmed that the temperature control state of the blood gas biochemical analyzer is in a normal state. In this way, according to the ambient temperatures and heating element temperatures corresponding to a plurality of time points respectively, a plurality of ambient temperature filtering results and a plurality of heating element temperature filtering results can be obtained. As long as each heating element temperature filtering result meets the heating element threshold temperature under the corresponding ambient temperature filtering result, and the air duct temperature corresponding to the current time also meets the air duct threshold temperature range, it can ensure that the temperature control state of the blood gas biochemical analyzer is in a normal state, thereby improving the accuracy of subsequent measurement data.

Description

Technical Field

[0001] The present invention relates to the technical field of data processing, and in particular, to a method for judging temperature abnormality and a method for data correction of a blood gas and biochemical analyzer. Background Art

[0002] A blood gas and biochemical analyzer uses a biosensor to measure relevant indicators such as the acidity and carbon dioxide partial pressure in an artery. After the sample to be tested (blood) is separated from the human body, its temperature will change under the influence of the external environment. In the prior art, a heating mechanism is arranged inside the blood gas and biochemical analyzer to heat the test card, so that the enzyme activity on the biosensor can reach the best state as much as possible, and the temperature of the sample to be tested in the test card can be closer to the temperature of the blood in the human body, thereby improving the measurement accuracy.

[0003] However, temperature control and maintenance is a continuous process. During the test process, it is impossible to determine whether the temperature control and maintenance inside the blood gas and biochemical analyzer has been completed at this time. If the test is directly carried out without completing the temperature control and maintenance, there will be a deviation between the blood temperature in the test card and the blood temperature in the human body, which will lead to a deviation between the measured value of the gas in the blood and the actual value. And the impedance of the biosensor is affected by temperature. The impedance corresponding to the same concentration of the test solution is different at different temperatures, thus affecting the accuracy of the test result. Summary of the Invention

[0004] The purpose of the present invention is to provide a method for judging temperature abnormality and a method for data correction of a blood gas and biochemical analyzer to ensure that the temperature control state of the blood gas and biochemical analyzer is in a normal state, thereby improving the accuracy of the test result.

[0005] A method for judging temperature abnormality of a blood gas and biochemical analyzer provided by the present invention, a heating sheet is arranged at a preset position of the test card of the blood gas and biochemical analyzer; the heating sheet is used to heat the test card; the method includes: obtaining the ambient temperature and the heating sheet temperature corresponding to multiple time points respectively within a specified time period determined based on the current time; determining multiple ambient temperature filtering results based on the multiple ambient temperatures; determining multiple heating sheet temperature filtering results based on the multiple heating sheet temperatures; obtaining the heating sheet threshold temperature corresponding to each ambient temperature filtering result from a preset first temperature relationship table; wherein, the first temperature relationship table includes the heating sheet threshold temperatures corresponding to multiple ambient temperatures respectively; if each current heating sheet temperature filtering result meets the corresponding heating sheet threshold temperature, obtaining the air duct temperature corresponding to the current time; wherein, the air duct temperature is used to represent the temperature of the internal air duct of the blood gas and biochemical analyzer; if the air duct temperature belongs to a preset air duct threshold temperature range, it is confirmed that the temperature control state of the blood gas and biochemical analyzer is in a normal state.

[0006] Further, the air duct threshold temperature range is obtained in the following manner: obtaining the current ambient temperature corresponding to the current time; obtaining the air duct threshold temperature range corresponding to the current ambient temperature from a preset second temperature relation table; wherein, the second temperature relation table includes air duct threshold temperature ranges corresponding to multiple ambient temperatures respectively.

[0007] Further, based on multiple ambient temperatures, multiple ambient temperature filtering results are determined; the steps of determining multiple heating element temperature filtering results based on multiple heating element temperatures include: performing filtering processing on the obtained multiple ambient temperatures to obtain multiple ambient temperature filtering results; performing filtering processing on the obtained multiple heating element temperatures to obtain multiple heating element temperature filtering results.

[0008] A data correction method for a blood gas biochemical analyzer provided by the present invention, the test card of the blood gas biochemical analyzer corresponding to multiple electrodes; the method includes: when it is confirmed that the temperature control state of the blood gas biochemical analyzer is in a normal state, for each electrode, determining the electrode temperature of the electrode according to the current ambient temperature and / or the current heating element temperature; wherein, the method described in any one of claims 1-3 is used to confirm whether the temperature control state of the blood gas biochemical analyzer is in a normal state; applying an excitation signal to a sample to be tested to obtain a response signal; according to the response signal and a preset first mathematical model, calculating a component test result of a specified component in the sample to be tested at a standard electrode temperature; wherein, the first mathematical model is a mathematical model determined based on the standard electrode temperature; if the electrode temperature is different from the standard electrode temperature, compensating and correcting the component test result according to a preset second mathematical model to obtain a component correction result of the specified component at the electrode temperature; if the electrode temperature is the same as the standard electrode temperature, determining the component test result as the component correction result.

[0009] Further, the response signal obtained by applying an excitation signal to the sample to be tested is an impedance modulus value, and the steps for obtaining the impedance modulus value include: applying an excitation signal to the sample to be tested to obtain an impedance spectrum; determining a complex function based on the impedance spectrum; calculating the impedance modulus value according to the imaginary part and the real part of the complex function.

[0010] Further, the first mathematical model is as follows:

[0011] C M-pre = k*Z + b;

[0012] The second mathematical model is as follows:

[0013] C M = ;

[0014] Among them, C M-pre is the component test result of the specified component M in the sample to be tested at the standard electrode temperature obtained by calculation; both k and b are coefficients; Z is the impedance modulus value; C M is the component correction result of the specified component M at the electrode temperature; T is the electrode temperature; GR M is the average relative change value.

[0015] Furthermore, the method for establishing the first mathematical model includes: obtaining test liquid samples with different concentration gradients pre-configured, and measuring the impedance modulus values corresponding to the test liquid samples at different concentration gradients through a blood gas and biochemical analyzer; wherein, the blood gas and biochemical analyzer is located in a constant temperature and humidity chamber, and the temperature of the constant temperature and humidity chamber is set to make the electrode temperature reach the standard electrode temperature; fitting the concentration of the test liquid samples and the impedance modulus values by linear fitting to obtain the first mathematical model at the standard electrode temperature.

[0016] Furthermore, the method for establishing the second mathematical model includes: establishing multiple temperature intervals based on the standard electrode temperature; calculating the standard sample concentration value of the test liquid sample through the first mathematical model at the standard electrode temperature; calculating the component test results corresponding to the test liquid samples with the same concentration at the end point temperatures of the temperature intervals according to the first mathematical model; calculating the deviation results between the component test results and the standard sample concentration value; calculating the difference between the electrode temperature and the standard electrode temperature to obtain a difference result; calculating the ratio of the deviation result to the difference result to obtain the average relative change value; obtaining the second mathematical model based on the average relative change value, the electrode temperature, and the standard electrode temperature to compensate and correct the component test results to obtain the component correction result of the specified component at the electrode temperature.

[0017] Furthermore, the step of determining the electrode temperature of each electrode according to the current ambient temperature and / or the current heating sheet temperature includes: for each electrode, if the electrode is located outside the test card, calculating the electrode temperature of the electrode based on the current ambient temperature and a preset first fitting relationship.

[0018] Furthermore, the specified component is HCT.

[0019] A temperature anomaly determination device for a blood gas and biochemical analyzer provided by the present invention. A heating sheet is provided at a preset position of a test card of the blood gas and biochemical analyzer; the heating sheet is used to heat the test card; the device includes: a first acquisition module, configured to acquire the ambient temperature and the heating sheet temperature respectively corresponding to multiple time points within a specified time period determined based on the current time; a first determination module, configured to determine multiple ambient temperature filtering results based on the multiple ambient temperatures, and determine multiple heating sheet temperature filtering results based on the multiple heating sheet temperatures; a second acquisition module, configured to acquire the heating sheet threshold temperature corresponding to each ambient temperature filtering result from a preset first temperature relationship table; wherein, the first temperature relationship table includes the heating sheet threshold temperatures respectively corresponding to multiple ambient temperatures; a third acquisition module, configured to, if each current heating sheet temperature filtering result conforms to the corresponding heating sheet threshold temperature, acquire the air duct temperature corresponding to the current time; wherein, the air duct temperature is used to represent the temperature of the internal air duct of the blood gas and biochemical analyzer; a confirmation module, configured to, if the air duct temperature belongs to a preset air duct threshold temperature range, confirm that the temperature control state of the blood gas and biochemical analyzer is in a normal state.

[0020] A data correction device for a blood gas and biochemical analyzer provided by the present invention. The test card of the blood gas and biochemical analyzer corresponds to multiple electrodes; the device includes: a second determination module, configured to, when it is confirmed that the temperature control state of the blood gas and biochemical analyzer is in a normal state, determine the electrode temperature of each electrode according to the current ambient temperature and / or the current heating sheet temperature; wherein, the method described in any one of the above is used to confirm whether the temperature control state of the blood gas and biochemical analyzer is in a normal state; an excitation module, configured to apply an excitation signal to a test sample to obtain an impedance modulus value; a calculation module, configured to calculate a component test result of a specified component in the test sample at a standard electrode temperature according to the impedance modulus value and a preset first mathematical model; wherein, the first mathematical model is a mathematical model determined based on the standard electrode temperature; a correction module, configured to, if the electrode temperature is different from the standard electrode temperature, perform compensation correction on the component test result according to a preset second mathematical model to obtain a component correction result of the specified component at the electrode temperature; a third determination module, configured to, if the electrode temperature is the same as the standard electrode temperature, determine the component test result as the component correction result.

[0021] An electronic device provided by the present invention includes a processor and a memory. The memory stores machine-executable instructions that can be executed by the processor. The processor executes the machine-executable instructions to implement the temperature anomaly determination method for the blood gas and biochemical analyzer described in any one of the above, or the data correction method for the blood gas and biochemical analyzer described in any one of the above.

[0022] The temperature anomaly judgment method and data correction method for a blood gas and biochemical analyzer provided by the present invention obtain the ambient temperature and heating element temperature corresponding to multiple time points respectively within a specified time period determined based on the current time; perform filtering processing on multiple ambient temperatures to obtain multiple filtered ambient temperature results; perform filtering processing on multiple heating element temperatures to obtain multiple filtered heating element temperature results; obtain the heating element threshold temperature corresponding to each filtered ambient temperature result from a preset first temperature relationship table; wherein, the first temperature relationship table includes the heating element threshold temperatures corresponding to multiple ambient temperatures respectively; if each filtered heating element temperature result meets the corresponding heating element threshold temperature, obtain the air duct temperature corresponding to the current time; wherein, the air duct temperature is used to represent the temperature of the internal air duct of the blood gas and biochemical analyzer; if the air duct temperature belongs to a preset air duct threshold temperature range, confirm that the temperature control state of the blood gas and biochemical analyzer is in a normal state. In this way, based on the ambient temperature and heating element temperature corresponding to multiple time points respectively, multiple filtered ambient temperature results and multiple filtered heating element temperature results can be obtained. As long as each filtered heating element temperature result meets the heating element threshold temperature under the corresponding filtered ambient temperature result, and the air duct temperature corresponding to the current time also meets the air duct threshold temperature range, it can ensure that the temperature control state of the blood gas and biochemical analyzer is in a normal state, thereby improving the accuracy of subsequent measurement data. BRIEF DESCRIPTION OF THE DRAWINGS

[0023] In order to more clearly illustrate the specific embodiments of the present invention or the technical solutions in the prior art, the following will briefly introduce the drawings required for use in the description of the specific embodiments or the prior art. Obviously, the drawings in the following description are some embodiments of the present invention. For those of ordinary skill in the art, without creative efforts, other drawings can also be obtained based on these drawings.

[0024] Figure 1 It is a flowchart of a temperature anomaly judgment method for a blood gas and biochemical analyzer provided by an embodiment of the present invention;

[0025] Figure 2 It is a schematic diagram of a first temperature relationship table provided by an embodiment of the present invention; Figure 3 It is a flowchart of a data correction method for a blood gas and biochemical analyzer provided by an embodiment of the present invention;

[0026] Figure 4 It is an experimental data graph of the HCT electrode temperature and the ambient temperature provided by an embodiment of the present invention;

[0027] Figure 5 It is a linear fitting graph of the HCT electrode temperature and the ambient temperature provided by an embodiment of the present invention;

[0028] Figure 6A schematic diagram of experimental table data provided by an embodiment of the present invention;

[0029] Figure 7 A schematic diagram of a fitting curve provided by an embodiment of the present invention;

[0030] Figure 8 A flowchart of another data correction method for a blood gas biochemical analyzer provided by an embodiment of the present invention;

[0031] Figure 9 A schematic diagram of a temperature control system for a blood gas biochemical analyzer provided by an embodiment of the present invention;

[0032] Figure 10 A schematic diagram of the structure of a temperature anomaly judgment device for a blood gas biochemical analyzer provided by an embodiment of the present invention;

[0033] Figure 11 A schematic diagram of the structure of a data correction device for a blood gas biochemical analyzer provided by an embodiment of the present invention;

[0034] Figure 12 A schematic diagram of the structure of an electronic device provided by an embodiment of the present invention. Detailed implementation manners

[0035] Next, the technical solutions of the present invention will be clearly and completely described in conjunction with the embodiments. Obviously, the described embodiments are some, but not all, of the embodiments of the present invention. All other embodiments obtained by those of ordinary skill in the art based on the embodiments of the present invention without creative efforts shall fall within the protection scope of the present invention.

[0036] A blood gas biochemical analyzer can use a biosensor to measure relevant indicators such as the pH value of blood in the artery, partial pressure of carbon dioxide (P CO2 ), partial pressure of oxygen (P O2 ), lac (lactic acid), glu (blood glucose) and the like in a relatively short time. During the detection, after the biosensor contacts the corresponding components in the sample to be measured, an electrochemical reaction occurs, generating an electrical signal. By processing the electrical signal, the indicators of various components of human blood can be calculated.

[0037] After the sample to be measured (blood) is separated from the human body, it is affected by the external environment and the temperature will change. The dissolution of gases (CO2 and O2) in blood is affected by temperature. If the temperature difference between the test environment and the human body environment is large, it will also affect the test accuracy.

[0038] The activity of the enzyme on the biosensor is also affected by temperature. When the temperature is too high or too low, the electrochemical reaction is insufficient, and the obtained electrical signal is inaccurate, ultimately leading to deviations in the test results. In particular, the enzyme activities of O2, lac, and glu biosensors are most easily affected by temperature.

[0039] A blood gas biochemical analyzer in the related art can heat the test card up and down, and multiple temperature sensors are arranged inside the blood gas biochemical analyzer, namely a first temperature sensor, a second temperature sensor, and a third temperature sensor, which are respectively arranged on the test card base assembly, at the air inlet of the fan, and at the opening on the right side of the housing. The system collects the values of these three temperature sensors, conducts data analysis and processing, and controls the rotation speed of the fan by adjusting PWM (Pulse Width Modulation), so that the temperature inside the housing can be kept in dynamic balance, thereby ensuring the accuracy of the test. However, this method mainly has the following defects:

[0040] Defect 1. Lack of a function to judge whether the temperature control is abnormal; this technology only realizes the overall temperature control inside the blood gas biochemical analyzer. Temperature control maintenance is a continuous process, but during the test, it is not known whether the temperature control inside the blood gas biochemical analyzer has been completed at this time. If the test is directly carried out without completion, there will be a deviation between the blood temperature in the test card and the blood temperature in the human body. The solubility of gas in blood is different at different temperatures, which will lead to a deviation between the measured value of the gas in the blood and the actual value.

[0041] Defect 2: Unable to calculate the actual value of the index based on temperature compensation; during the actual operation process, due to the temperature conduction and loss of the heating structure, as well as the interference of the heat generated by the electronic devices inside the blood gas biochemical analyzer, the heating device cannot accurately heat the biosensor to the set temperature, thus unable to ensure that the biosensor can reach the best activity, which will lead to a deviation between the measured value and the actual value. Although the first temperature sensor, the second temperature sensor, and the third temperature sensor are set to collect temperature data and the rotation speed of the fan is controlled through data analysis, it is only used for the overall temperature control inside the entire blood gas biochemical analyzer and cannot achieve accurate temperature measurement of the biosensor with high temperature requirements.

[0042] During the test, the conduction of the electrical signal of the biosensor is also affected by temperature, resulting in an offset in the measurement result (the electrical signal generated by the test is very small, for example, the response current of the oxygen sensor is -0.6uA - -3uA). Based on this, the embodiments of the present invention provide a method for judging temperature abnormality and a method for data correction of a blood gas biochemical analyzer. This technology can be applied to applications that require using a blood gas biochemical analyzer to measure the components in a sample to be tested.

[0043] For the convenience of understanding this embodiment, first, a method for judging temperature abnormality of a blood gas biochemical analyzer disclosed in the embodiments of the present invention will be introduced. A heating sheet is provided at a preset position of the test card of the blood gas biochemical analyzer; the heating sheet is used to heat the test card; a blood gas biochemical analyzer is an instrument that can use electrodes to measure related indicators such as the pH value, partial pressure of carbon dioxide (P CO2 ) and partial pressure of oxygen (P O2 ) in a test sample in a relatively short time. The above-mentioned preset position can be above or below the test card, etc., and can be specifically set according to actual needs; by heating the test card with the heating sheet, the temperature of the test sample in the test card, such as blood, can be made closer to the temperature of blood in the human body; as Figure 1 shown, the method includes the following steps:

[0044] Step S102, obtain the ambient temperature and the heating sheet temperature corresponding to multiple time points respectively within a specified time period determined based on the current time.

[0045] The above-mentioned specified time period can be set according to actual monitoring accuracy requirements. For example, when the number of time points is the same, if the specified time period is a relatively short time, the monitoring accuracy will be relatively higher; if the specified time period is a relatively long time, the monitoring accuracy will be relatively lower; the number of the above-mentioned time points can also be set according to actual needs. For example, 5 or 7 time points can be evenly selected from the specified time period, etc.; the above-mentioned ambient temperature can be collected by a ventilation port temperature probe, which is usually located on the surface of the blood gas biochemical analyzer, close to the outer shell of the device, and can monitor and record the external ambient temperature in real time as the basis for subsequent temperature compensation. The above-mentioned heating sheet temperature can be collected by an NTC (Negative Temperature Coefficient). If the heating sheet is located below the card insertion position, the NTC can be located below the card insertion position, close to the surface of the heating sheet, and is used to monitor the temperature change of the heating sheet. In order to accurately measure the index values of various components in the blood, it is usually necessary to heat the test card to make the temperature of the test card consistent with the human body temperature. In this case, it is necessary to first confirm whether the temperature control of the blood gas biochemical analyzer is normal and effective. At this time, multiple time points within the specified time period can be determined first, and the ambient temperature and the heating sheet temperature collected at each time point can be obtained.

[0046] Step S104, based on the multiple ambient temperatures, determine multiple ambient temperature filtering results; based on the multiple heating sheet temperatures, determine multiple heating sheet temperature filtering results.

[0047] In actual implementation, after obtaining multiple ambient temperatures and multiple heater temperatures, multiple ambient temperature filtering results and multiple heater temperature filtering results can be further determined; for example, they can be determined through filtering processing methods such as median filtering and mean filtering.

[0048] Step S106, obtain the heater threshold temperature corresponding to each ambient temperature filtering result from a preset first temperature relationship table; wherein, the first temperature relationship table includes heater threshold temperatures corresponding to multiple ambient temperatures respectively.

[0049] In the first temperature relationship table, the heater threshold temperatures corresponding to different ambient temperatures are usually different. Each heater threshold temperature can be a specific temperature value or a temperature range, which can be specifically set according to actual requirements; in actual implementation, the first temperature relationship table can be pre-configured, and the heater temperature threshold corresponding to each ambient temperature filtering result is selected from this first temperature relationship table.

[0050] In this embodiment, the heater temperature of the blood gas and biochemical analyzer is controlled according to the ambient temperature filtering result. The specific control process is implemented through the PID algorithm. The first temperature relationship table is as Figure 2 shown. Each ambient temperature (corresponding to the above ambient temperature filtering result) corresponds to a heater temperature. When the ambient temperature filtering result is obtained, the current heater temperature filtering result is collected, and the current heater temperature filtering result is compared with the heater temperature corresponding to this ambient temperature in the first temperature relationship table. If the current heater temperature filtering result exceeds the heater temperature, the temperature control is abnormal; otherwise, the temperature control is normal.

[0051] Step S108, if each heater temperature filtering result meets the corresponding heater threshold temperature, obtain the air duct temperature corresponding to the current time; wherein, the air duct temperature is used to represent the temperature of the internal air duct of the blood gas and biochemical analyzer.

[0052] Determine whether the temperature filtering result of each heating sheet conforms to the threshold temperature of the heating sheet under the corresponding ambient temperature filtering result. For example, if the threshold temperature of the heating sheet is a specific temperature value, when the temperature filtering result of the heating sheet does not exceed the threshold temperature of the heating sheet, it can be considered that the temperature filtering result of the heating sheet conforms to the threshold temperature of the heating sheet; if the threshold temperature of the heating sheet is a temperature range, when the temperature filtering result of the heating sheet belongs to this temperature range, it can be considered that the temperature filtering result of the heating sheet conforms to the threshold temperature of the heating sheet, etc.; if it is determined that the temperature filtering result of each heating sheet conforms to the threshold temperature of the heating sheet under the corresponding ambient temperature filtering result, the air duct temperature corresponding to the current time can be obtained. This air duct temperature can be represented by Tw. The air duct temperature can be collected by a channel temperature probe. This channel temperature probe is usually suspended above the test card insertion position of the blood gas and biochemical analyzer and is located in the air duct for equipment ventilation and at the central position of the equipment. On the one hand, this channel temperature probe is affected by the combined action of the heating of the heating sheet and the heat dissipation of the fan, and on the other hand, it is affected by the heat dissipation of other components inside the blood gas and biochemical analyzer. It can monitor the temperature change of the blood gas and biochemical analyzer during the entire measurement process. By collecting the temperature change of this channel temperature probe, it can be judged whether the blood gas and biochemical analyzer is in a normal working state.

[0053] Step S110, if the air duct temperature belongs to the preset air duct threshold temperature range, confirm that the temperature control state of the blood gas and biochemical analyzer is in a normal state.

[0054] Since the air duct temperature is constantly affected by air duct ventilation and heating sheet heat dissipation during the measurement process and is in a fluctuating state, during actual testing, as long as it is ensured that its fluctuation range is within the specified air duct threshold temperature range, it can be confirmed that the temperature control state of the blood gas and biochemical analyzer is in a stable normal state.

[0055] Taking the air duct threshold temperature range as [Tmin, Tmax] as an example, if the air duct temperature belongs to [Tmin, Tmax], continue with temperature correction; otherwise, judge that the temperature control is abnormal and end the test. The temperature of the heating sheet and the ambient temperature are controlled by the PID algorithm, that is, the temperature of the heating sheet is adjusted by the ambient temperature.

[0056] It should be noted that the above Tmin and Tmax are obtained through experimental tests and are jointly determined by the heating sheet temperature and the ambient temperature. Therefore, under different ambient temperatures, the air duct threshold temperature range usually varies. [Tmin, Tmax] is a temperature change range. When the ambient temperature is determined, during the entire test process, Tw fluctuates but does not exceed these two upper and lower limits. If the fluctuation exceeds the range, either the ambient temperature is unstable or there is a problem with the machine's temperature control, generally within 3°C.

[0057] Changes in the ambient temperature and the temperature of the heating element will directly affect the temperature compensation effect. Therefore, it is necessary to continuously record the complete data during the entire measurement process, while the Tw temperature probe only needs to record the instant temperature. At the same time, the ambient temperature will be stored in the device memory until the target value analysis is completed, and the Tw temperature only needs to be calculated instantaneously and refreshed in real time.

[0058] When specifically implemented, the threshold temperature range of the air duct can be obtained through the following steps a and b:

[0059] Step a: Obtain the current ambient temperature corresponding to the current time.

[0060] Step b: Obtain the threshold temperature range of the air duct corresponding to the current ambient temperature from the preset second temperature relation table; wherein, the second temperature relation table includes the threshold temperature ranges of the air duct corresponding to multiple ambient temperatures respectively.

[0061] In the second temperature relation table, the threshold temperature ranges of the air duct corresponding to different ambient temperatures are usually different; in actual implementation, the second temperature relation table can be pre-configured. After obtaining the air duct temperature corresponding to the current time, the threshold temperature range of the air duct corresponding to the current ambient temperature can be selected from this second temperature relation table.

[0062] (1) Theoretically, the human body temperature is generally around 37 °C. Therefore, the blood gas analyzer is kept at around 37 °C to simulate the human body temperature; at the same time, the external ambient temperature is in a stable state during measurement; overall, Tw is actually in a dynamic equilibrium state within a fixed temperature range.

[0063] During the preliminary experiment process, according to the measurement temperature range (10 °C - 30 °C) of the blood gas analyzer, a total of 31 temperature steps were divided, and the changes in the channel temperature Tw were measured at different external ambient temperatures to obtain different temperature ranges [Tmin, Tmax].

[0064]

[0065]

[0066] …

[0067]

[0068] (3) During the actual measurement process, the Tw temperature can be monitored in real time, and median filtering is performed on the Tw collected temperature at a time interval of 3 s. Compare Tw with [Tmin, Tmax] at this temperature. When it exceeds this range, it can be determined that the temperature of the blood gas analyzer is abnormal, or a preset number of times can be set. For example, when the situation of exceeding the range occurs more than 3 times, it is determined that the temperature of the blood gas analyzer is abnormal.

[0069] For the temperature anomaly determination method of the above blood gas analyzer, obtain the ambient temperature and the heating element temperature corresponding to multiple time points respectively within a specified time period determined based on the current time; determine multiple ambient temperature filtering results based on the multiple ambient temperatures; determine multiple heating element temperature filtering results based on the multiple heating element temperatures; obtain the heating element threshold temperature corresponding to each ambient temperature filtering result from a preset first temperature relationship table; wherein, the first temperature relationship table includes the heating element threshold temperatures corresponding to multiple ambient temperatures respectively; if each heating element temperature filtering result meets the corresponding heating element threshold temperature, obtain the air duct temperature corresponding to the current time; wherein, the air duct temperature is used to represent the temperature of the internal air duct of the blood gas analyzer; if the air duct temperature belongs to a preset air duct threshold temperature range, confirm that the temperature control state of the blood gas analyzer is in a normal state. In this way, multiple ambient temperature filtering results and multiple heating element temperature filtering results can be obtained based on the ambient temperature and the heating element temperature corresponding to multiple time points respectively. As long as each heating element temperature filtering result meets the heating element threshold temperature under the corresponding ambient temperature filtering result, and the air duct temperature corresponding to the current time also meets the air duct threshold temperature range, it can ensure that the temperature control state of the blood gas analyzer is in a normal state, thereby improving the accuracy of subsequent measurement data.

[0070] The embodiment of the present invention also provides another temperature anomaly determination method for a blood gas analyzer. This method is implemented based on the method of the above embodiment, and this method focuses on describing the specific process of determining multiple ambient temperature filtering results based on the multiple ambient temperatures and determining multiple heating element temperature filtering results based on the multiple heating element temperatures.

[0071] Specifically, filtering processing can be performed on the obtained multiple ambient temperatures to obtain multiple ambient temperature filtering results; filtering processing can be performed on the obtained multiple heating element temperatures to obtain multiple heating element temperature filtering results.

[0072] The above filtering processing methods usually include median filtering, mean filtering, etc.; in actual implementation, in order to reduce the computing load of the device and obtain a stable temperature value at the same time, after obtaining the ambient temperature and the heating element temperature corresponding to multiple time points respectively, median filtering can be performed on the multiple ambient temperatures and then the mean value can be taken to obtain multiple ambient temperature filtering results, which can be represented by Te; median filtering can be performed on the multiple heating element temperatures and then the mean value can be taken to obtain multiple heating element temperature filtering results, which can be represented by Tn. The number of multiple ambient temperature filtering results and the number of multiple heating element temperature filtering results are usually the same, and moreover, the multiple ambient temperature filtering results and the multiple heating element temperature filtering results are usually in one-to-one correspondence, that is, one ambient temperature filtering result can correspond to one heating element temperature filtering result.

[0073] For ease of understanding, taking Tn as an example, after obtaining the temperatures of multiple heating elements, the following steps can be carried out:

[0074] Step 1. Perform preliminary median filtering with s as the window;

[0075] T = Med{t i-s ,…,t,…,t i+s};

[0076] Step 2. After median filtering, perform mean filtering in units of window v;

[0077] Tn = Avg{T i-v ,…,T,…,T i+v};

[0078] Among them, s and v are obtained through pre-tests and adjusted according to the number of abnormal points in the temperature data, generally set to about 5 and 7; for example, there are a total of 10 data corresponding to the temperatures of heating elements, the window is 5, starting from the first heating element temperature data, taking the temperature data of the 1st - 5th heating elements according to the window for median filtering to obtain the first median filtering result; then starting from the second heating element temperature data, taking the data of the 2nd - 6th according to the window for median filtering to obtain the second median filtering result; and so on until the window reaches the last heating element temperature data; another example, there are a total of 10 median filtering results, the window is 7, starting from the first median filtering result, taking the 1st - 7th median filtering results according to the window for mean filtering to obtain the first mean filtering result; then starting from the second median filtering result, taking the 2nd - 8th median filtering results according to the window for mean filtering to obtain the second mean filtering result; and so on until the window reaches the last median filtering result to obtain multiple filtered results of heating element temperatures. For specific details, reference can be made to related technologies and will not be elaborated here.

[0079] The above Step 1 is mainly to eliminate abnormal points such as jump values in the temperature data and reduce the noise of the signal. In Step 2, the data is further smoothed and denoised to obtain the temperature stable values in different time periods for subsequent temperature analysis.

[0080] The embodiment of the present invention also provides a data correction method for a blood gas and biochemical analyzer. This method is implemented on the basis of the method in the above embodiment. In this method, the test card of the blood gas and biochemical analyzer corresponds to multiple electrodes. For example, it may include an hct electrode, a CO2 electrode, a lac electrode, an O2 electrode, a glu electrode, etc. Different electrodes can be used to measure the indexes of different components in a sample to be tested, such as blood. The positions of different electrodes in the blood gas and biochemical analyzer are usually different. For example, some electrodes are located outside the test card, some are located in the middle of the test card, and some are located inside the blood gas and biochemical analyzer and are heated by a heating sheet, etc. As Figure 3 shown, the method includes the following steps:

[0081] Step S302, when it is confirmed that the temperature control state of the blood gas and biochemical analyzer is in a normal state, for each electrode, determine the electrode temperature of the electrode according to the current ambient temperature and / or the current heating sheet temperature; wherein, the method in the above embodiment is used to confirm whether the temperature control state of the blood gas and biochemical analyzer is in a normal state.

[0082] When it is confirmed that the temperature control state of the blood gas and biochemical analyzer is in a normal state according to the method in the foregoing embodiment, the blood gas and biochemical analyzer can be used to measure the indexes of each component in the sample to be tested, and the measured indexes are corrected so that the corrected index values are closer to the true values. Specifically, the electrode temperature of the electrode is determined according to the current ambient temperature and / or the current heating sheet temperature, and the electrode temperature of each electrode is calculated.

[0083] Step S304, apply an excitation signal to the sample to be tested to obtain a response signal.

[0084] The sample to be tested, the standard electrode temperature, and the standard sample concentration value at the standard electrode temperature can be obtained. For a blood gas and biochemical analyzer, the sample to be tested usually refers to blood, such as human blood, etc. The above standard electrode temperature usually refers to the electrode temperature in a standard test environment, such as 23°C, etc. The above standard sample concentration value is usually a pre-set standard sample concentration value corresponding to the standard electrode temperature. Each electrode corresponds to a different measured component, and the standard sample concentration values corresponding to each measured component are usually also different.

[0085] The above excitation signal can be an alternating current signal excitation with a fixed period, etc. In actual implementation, in a blood gas and biochemical analyzer, an electrochemical method can be used to measure different components in the sample to be tested. The principle is to apply an alternating current signal excitation with a fixed period to the blood to obtain a corresponding response signal, and the response signal can be an impedance modulus value.

[0086] Step S306: Calculate the component test result of the specified component in the sample to be tested at the standard electrode temperature according to the response signal and the preset first mathematical model; wherein, the first mathematical model is a mathematical model determined based on the standard electrode temperature.

[0087] The above-mentioned specified component can be the red blood cell component in the sample to be tested, etc.; different electrodes usually measure different components; after obtaining the impedance modulus value, the impedance modulus value can be substituted into the preset first mathematical model, and according to the first mathematical model, the component test result of the specified component in the sample to be tested is calculated. Since the first mathematical model is a mathematical model determined based on the standard electrode temperature, the obtained component test result is the result corresponding to the standard electrode temperature.

[0088] Step S308: If the electrode temperature is different from the standard electrode temperature, compensate and correct the component test result according to the preset second mathematical model to obtain the component correction result of the specified component at the electrode temperature.

[0089] Since the electrode temperature may be the same as or different from the standard electrode temperature, if the electrode temperature is different from the standard electrode temperature, the component test result obtained through the above steps usually differs from the actual component result, and it is necessary to compensate the calculated component test result. Specifically, according to the component test result, the standard sample concentration value, the electrode temperature, and the standard electrode temperature, the component test result is compensated and corrected according to the preset second mathematical model to obtain the compensated component correction result, which is closer to the actual component result of the specified component at the electrode temperature.

[0090] Step S310: If the electrode temperature is the same as the standard electrode temperature, determine the component test result as the component correction result.

[0091] If the electrode temperature is the same as the standard electrode temperature, since the first mathematical model is a mathematical model determined based on the standard electrode temperature, the obtained component test result is the result corresponding to the standard electrode temperature. At this time, the calculated component test result can be directly determined as the component correction result of the specified component.

[0092] The above data calibration method for a blood gas and biochemical analyzer, when it is confirmed that the temperature control state of the blood gas and biochemical analyzer is in a normal state, for each electrode, determine the electrode temperature of the electrode according to the current ambient temperature and / or the current heating sheet temperature; apply an excitation signal to the sample to be tested to obtain a response signal; according to the response signal and a preset first mathematical model, calculate the component test result of the specified component in the sample to be tested at the standard electrode temperature; wherein, the first mathematical model is a mathematical model determined based on the standard electrode temperature; if the electrode temperature is different from the standard electrode temperature, compensate and correct the component test result according to a preset second mathematical model to obtain the component calibration result of the specified component at the electrode temperature; if the electrode temperature is the same as the standard electrode temperature, determine the component test result as the component calibration result. In this method, on the premise of confirming that the temperature control state of the blood gas and biochemical analyzer is in a normal state, the component test result of the specified component in the sample to be tested can be determined according to the first mathematical model, and by comparing the electrode temperature with the standard electrode temperature, the component test result is corrected to obtain the corresponding component calibration result, ensuring that the component calibration result is closer to the actual true value and improving the accuracy of data measurement.

[0093] The embodiment of the present invention also provides another data calibration method for a blood gas and biochemical analyzer, which is implemented on the basis of the method of the above embodiment, and the method includes the following steps:

[0094] Step 1, when it is confirmed that the temperature control state of the blood gas and biochemical analyzer is in a normal state, for each electrode, determine the electrode temperature of the electrode according to the current ambient temperature and / or the current heating sheet temperature; wherein, use the method of the above embodiment to confirm whether the temperature control state of the blood gas and biochemical analyzer is in a normal state.

[0095] The step of determining the electrode temperature of each electrode according to the current ambient temperature and / or the current heating sheet temperature includes: for each electrode, if the electrode is located outside the test card, calculate the electrode temperature of the electrode based on the current ambient temperature and a preset first fitting relationship.

[0096] In a real measurement environment, the electrode temperature of the test card cannot be directly measured, and only the device temperature can be obtained. It is necessary to construct a relevant temperature model through preliminary tests to indirectly obtain the electrode temperature for subsequent temperature compensation.

[0097] If the electrode is located outside the test card, its solution temperature is mainly affected by the ambient temperature Te, and the correlation between the two is greater than 0.95: for the convenience of explanation, taking the hct electrode as an example, its first fitting relationship is as follows:

[0098] Thct = Te*a1^2 + Te*a2 + a3

[0099] Among them, Te represents the current ambient temperature; a1, a2, and a3 are coefficients.

[0100] If the electrode is located in the middle part of the test card, based on the current ambient temperature, the current heating sheet temperature, and the preset second fitting relationship, the electrode temperature of the electrode is calculated.

[0101] For some electrodes such as Na and CO2 located in the middle part of the test card, affected by the ambient temperature and the heating sheet temperature together, two temperatures are required as parameters for joint fitting. For the convenience of explanation, taking the Na electrode and the CO2 electrode as examples, their second fitting relationships are as follows:

[0102] TNa = Te*b1^2 + Te*b2 + Tn*b3^2 + Tn*b4 + b5

[0103] Tco2 = Te*d1^2 + Te*d2 + Tn*d3^2 + Tn*d4 + d5

[0104] Among them, Te represents the current ambient temperature; Tn represents the current heating sheet temperature; b1-b5, d1-d5 are all coefficients.

[0105] If the electrode is located inside the blood gas biochemical analyzer and is heated by the heating sheet, based on the current heating sheet temperature and the preset third fitting relationship, the electrode temperature of the electrode is calculated.

[0106] For example, the lac, O2, and glu electrodes are directly heated by the heating sheet and are located inside the blood gas biochemical analyzer during testing, and are basically not interfered by the ambient temperature. Therefore, their temperatures are only related to Tn. For the convenience of explanation, taking the lac electrode and the O2 electrode as examples, their third fitting relationships are as follows:

[0107] Tlac = Tn*e1^2 + Tn*e2 + e3;

[0108] Tglu = Tn*f1^2 + Tn*f2 + f3;

[0109] Among them, Tn represents the current heating sheet temperature; e1-e3, f1-f3 are all coefficients.

[0110] The HCT electrode is located on the outside of the test card and is affected by the ambient temperature.

[0111] To obtain the mathematical model of the HCT electrode temperature and the ambient temperature Te, a first fitting relationship needs to be established in the early stage of testing.

[0112] The specific method for establishing the first fitting relationship is as follows.

[0113] 1) Place the blood gas analyzer and the test card in a thermostatic and humidistatic chamber, keep the blood gas analyzer powered on, and rewarm for 60 - 90 minutes.

[0114] 2) Insert the card for cyclic testing, repeat 5 - 8 times in total, with a test interval of 1 - 2 minutes. During this period, do not remove the card or open the thermostatic and humidistatic chamber to prevent temperature convection.

[0115] 3) Record the temperature data and save it as Figure 4 shown. Note that the temperature of the blood gas analyzer and the temperature of the test card should correspond one - to - one in terms of time.

[0116] 4) Repeat the above process at temperature gradients of 12°C, 18°C, 22°C, 25°C, 27°C, and 30°C respectively to complete the experiment.

[0117] 5) Conduct linear fitting based on the temperature data, as shown in Figure 5 a schematic diagram of a fitting curve shown. Among them, the x - axis represents the ambient temperature Te; the y - axis represents the temperature of the HCT electrode on the test card.

[0118] 6) Through linear fitting by the least - squares method, k = 1.0155, b = - 0.0511, Thct = 1.015 * Te - 0.0511. The error between the HCT electrode temperature calculated by this linear function and the actual temperature value does not exceed ±3%.

[0119] Step 2: Apply an excitation signal to the sample to be measured to obtain a response signal.

[0120] The response signal obtained by applying an excitation signal to the sample to be measured is the impedance modulus value. The steps for obtaining the impedance modulus value can be achieved through the following steps A to C:

[0121] Step A: Apply an excitation signal to the sample to be measured to obtain an impedance spectrum.

[0122] Step B: Determine the complex function based on the impedance spectrum.

[0123] Step C: Calculate the impedance modulus value according to the imaginary part and the real part of the complex function.

[0124] By applying an alternating - current signal excitation with a fixed period to the sample to be measured, the corresponding impedance spectrum can be obtained. From the impedance spectrum, the complex function of admittance can be obtained. According to the imaginary part and the real part of this complex function, the impedance modulus value can be deduced, which can be specifically achieved through the following formula:

[0125] ;

[0126] where Z represents the impedance modulus value; z1 and z2 are respectively the values of the imaginary part and the real part of the complex function, and these values will change due to different blood oxygen levels.

[0127] Step 3: According to the response signal and a preset first mathematical model, calculate the component test result of the specified component in the sample to be tested at the standard electrode temperature; wherein, the first mathematical model is a mathematical model determined based on the standard electrode temperature.

[0128] In actual implementation, the above first mathematical model can be as follows:

[0129] C M-pre = k * Z + b;

[0130] Wherein, C M-pre is the component test result of the specified component M in the sample to be tested at the standard electrode temperature; both k and b are coefficients; Z is the impedance modulus value.

[0131] The method for establishing the above first mathematical model includes the following steps 30 and 31:

[0132] Step 30: Obtain test liquid samples with different concentration gradients configured in advance, and measure the impedance modulus values corresponding to the test liquid samples at different concentration gradients through a blood gas and biochemical analyzer; wherein, the blood gas and biochemical analyzer is located in a constant temperature and humidity chamber, and the temperature of the constant temperature and humidity chamber is set to make the electrode temperature reach the standard electrode temperature;

[0133] Step 31: Fit the concentration and impedance modulus value of the test liquid sample by using linear fitting to obtain the first mathematical model at the standard electrode temperature.

[0134] In actual implementation, the above specified component is usually HCT. Taking the specified component as HCT as an example, there is a significant correlation between the concentration of HCT and the modulus value and phase angle. The concentration can be deduced from the modulus value, and its corresponding first mathematical model is as follows:

[0135] C HCT-pre = k * Z + b;

[0136] Wherein, C HCT-pre is the component test result of HCT in the sample to be tested at the standard electrode temperature; both k and b are coefficients; Z is the impedance modulus value. k and b are respectively empirical parameters obtained by fitting at the standard electrode temperature (such as 23 °C) of the hct electrode. The fitting graph is shown in Table 1 below. Among them, at 23 °C, k = -5895, b = 5118, and the parameter values will change at different temperatures. For different specified components, the corresponding values of k and b are usually also different, and R2 represents the variance.

[0137] Table 1

[0138]

[0139] The determination methods of k and b can be as follows:

[0140] 1. Collect the corresponding relationship between different concentrations of HCT and Z at Thct = 23°C.

[0141] 2. Use the least squares method to linearly fit the data, and the linear equation is C HCT = k*Z + b; where,

[0142] ;

[0143] ;

[0144] Such as Figure 6 a schematic diagram of experimental table data as shown, including the HCT concentration value as the real data, the calculated HCT concentration as the concentration value calculated by the first mathematical model, and the error indicating the degree of difference between the calculated HCT concentration and the HCT concentration value; as Figure 7 a schematic diagram of a fitting curve as shown, where the x-axis represents the impedance modulus value Z; the y-axis represents the test result of the HCT component in the sample to be tested.

[0145] Through the least squares method linear fitting, k = -5958.7, b = 5118.9, and Chct = -5958*Z + 5118. The error between the HCT concentration value calculated by this linear function and the actual value does not exceed ±3%.

[0146] Before performing temperature compensation on HCT, first determine the fitting relationship between HCT concentration and Z at different temperatures. Some of the relationships are shown in Table 1. At different temperatures, there is an obvious linear relationship between HCT and Z. Therefore, it shows that the influence of temperature on HCT is linear and can be corrected by compensation.

[0147] Step 4, if the electrode temperature is different from the standard electrode temperature, compensate and correct the component test result according to the preset second mathematical model to obtain the component correction result of the specified component at the electrode temperature.

[0148] The second mathematical model is as follows:

[0149] C M = ;

[0150] where, C M is the component correction result of the specified component M at the electrode temperature; T is the electrode temperature; GR M is the average relative change value.

[0151] The establishment method of this second mathematical model includes the following steps 40 and 46:

[0152] Step 40, establish multiple temperature range segments based on the standard electrode temperature.

[0153] Step 41, calculate the standard sample concentration value of the test liquid sample through the first mathematical model at the standard electrode temperature.

[0154] Step 42, calculate the component test results corresponding to the test liquid samples with the same concentration at the endpoint temperatures of the temperature range segments according to the first mathematical model.

[0155] The above temperature range segments can be set according to the standard electrode temperature and combined with actual needs. The standard electrode temperature is usually included in this temperature range segment. For example, if the standard electrode temperature is 23 °C, the temperature range segments can be set as 20 °C - 25 °C, 21 °C - 26 °C, etc.; the number of temperature range segments can also be set as required. Generally, the more the number of temperature range segments, the higher the accuracy of the second mathematical model obtained because more data is collected.

[0156] For the test liquid samples with the same concentration, use the first mathematical model to calculate the corresponding component test results at the endpoint temperatures of the temperature range segments. For example, if the temperature range segment is 20 °C - 25 °C, use the first mathematical model to calculate the component test results corresponding to the test liquid sample at 20 °C, and use the first mathematical model to calculate the component test results corresponding to the test liquid sample at 25 °C. Whether it is 20 °C or 25 °C, the concentration of the test liquid sample is the same as the concentration of the test liquid in "calculating the standard sample concentration value of the HCT test liquid through the first mathematical model at the standard electrode temperature".

[0157] Step 43, calculate the deviation result between the component test result and the standard sample concentration value.

[0158] For the convenience of explanation, still taking the specified component as HCT as an example, in the case of the standard electrode temperature (such as 23 °C), the component test result of HCT is calculated through the first mathematical model, and the relative deviation between the component test result and the standard sample concentration value is calculated by the following formula:

[0159] ;

[0160] Among them, RE HCT represents the deviation result; HCT represents the component test result; HCT T=23℃ represents the standard sample concentration value.

[0161] Step 44, calculate the difference between the electrode temperature and the standard electrode temperature to obtain the difference result.

[0162] Step 45, calculate the ratio of the deviation result to the difference result to obtain the average relative change value.

[0163] The growth rate of HCT can be further calculated, which is the average relative change value of HCT concentration per 1°C change in temperature. The formula is as follows:

[0164] ;

[0165] Where GR represents the average relative change value; T represents the electrode temperature.

[0166] Step 46: Based on the average relative change value, the electrode temperature, and the standard electrode temperature, a second mathematical model is obtained to compensate and correct the component test result, and the component correction result of the specified component at the electrode temperature is obtained.

[0167] In actual implementation, when the electrode temperature is different from the standard electrode temperature, the component test result can be compensated and corrected according to the second mathematical model.

[0168] Taking the HCT component as an example, when the electrode temperature is different from the standard electrode temperature, the component test result can be compensated and corrected according to the second mathematical model. The corresponding second mathematical model is as follows:

[0169] ;

[0170] Where C HCT is the component correction result; T is the electrode temperature; GR HCT is the average relative change value corresponding to HCT.

[0171] Step Five: If the electrode temperature is the same as the standard electrode temperature, the component test result is determined as the component correction result.

[0172] Based on the above steps, the correction formula for HCT can be obtained as follows:

[0173] ;

[0174] To further understand the above embodiments, the following provides a flowchart of another data correction method for a blood gas biochemical analyzer as shown in Figure 8 First, test the sample and record the time series t, record the air duct temperature and refresh it; continuously record the ambient temperature and save it; continuously record the heating element temperature and save it; take the ambient temperature of the sample segment, take the mean value after median filtering as Te, take the heating element temperature sequence of the sample segment, and take the mean value after median filtering as Tn; judge whether each heating element temperature filtering result meets the corresponding heating element threshold temperature. If it meets the corresponding heating element threshold temperature, judge whether the air duct temperature belongs to the preset air duct threshold temperature range. If it belongs to the preset air duct threshold temperature range, based on the first mathematical model, calculate the component test result of the specified component at the standard electrode temperature, and determine the component correction result according to the component test result.

[0175] See Figure 9 the schematic diagram of the temperature control system of a blood gas and biochemical analyzer shown in the figure. Among them, the temperature control controller is sequentially connected to the main controller and the heating element. The main controller can send a temperature adjustment instruction to the temperature control controller. After receiving the temperature adjustment instruction, the temperature control controller controls the heating of the heating element through PID control according to the collected temperature of the heating element and the ambient temperature. The formula for controlling the temperature by the PID algorithm is as follows:

[0176] pid->out = (Kp * (Ek - Ek1)) + (Ki * Ek) + (Kd * (Ek - 2* Ek1 +Ek2));

[0177] Among them, pid->out is the output signal, which is 1%-100%, and is the percentage of the full power of the heater; Ek = target (target value) - actual (true value); the target value is set according to the preset value corresponding to the detected ambient temperature Te; the parameters are Kp = 0.1; Ki = 0.02; Kd = 0.0; Ek1 is the difference between the target value and the true value at the previous time point; Ek2 is the difference between the target value and the true value at the two previous time points.

[0178] For the above-mentioned data correction method of the blood gas and biochemical analyzer, on the premise of confirming that the temperature control state of the blood gas and biochemical analyzer is in a normal state, the component test result of the specified component in the sample to be tested can be determined according to the first mathematical model, and the component test result is corrected by comparing the electrode temperature with the standard electrode temperature to obtain the corresponding component correction result, which ensures that the component correction result is closer to the actual true value and improves the accuracy of data measurement.

[0179] An embodiment of the present invention provides a device for judging temperature abnormality of a blood gas and biochemical analyzer. A heating element is provided at a preset position of the test card of the blood gas and biochemical analyzer; the heating element is used to heat the test card; as Figure 10As shown in the figure, the device includes: a first acquisition module 100, configured to acquire the ambient temperature and the heating sheet temperature corresponding to multiple time points respectively within a specified time period determined based on the current time; a first determination module 101, configured to determine multiple ambient temperature filtering results based on the multiple ambient temperatures, and determine multiple heating sheet temperature filtering results based on the multiple heating sheet temperatures; a second acquisition module 102, configured to acquire the heating sheet threshold temperature corresponding to each ambient temperature filtering result from a preset first temperature relationship table, where the first temperature relationship table includes the heating sheet threshold temperatures corresponding to multiple ambient temperatures respectively; a third acquisition module 103, configured to acquire the air duct temperature corresponding to the current time if each current heating sheet temperature filtering result meets the corresponding heating sheet threshold temperature, where the air duct temperature is used to represent the temperature of the internal air duct of the blood gas and biochemical analyzer; a confirmation module 104, configured to confirm that the temperature control state of the blood gas and biochemical analyzer is in a normal state if the air duct temperature belongs to a preset air duct threshold temperature range.

[0180] The above temperature abnormality determination device of the blood gas and biochemical analyzer acquires the ambient temperature and the heating sheet temperature corresponding to multiple time points respectively within a specified time period determined based on the current time, determines multiple ambient temperature filtering results based on the multiple ambient temperatures, determines multiple heating sheet temperature filtering results based on the multiple heating sheet temperatures, acquires the heating sheet threshold temperature corresponding to each ambient temperature filtering result from a preset first temperature relationship table, where the first temperature relationship table includes the heating sheet threshold temperatures corresponding to multiple ambient temperatures respectively, acquires the air duct temperature corresponding to the current time if each heating sheet temperature filtering result meets the corresponding heating sheet threshold temperature, where the air duct temperature is used to represent the temperature of the internal air duct of the blood gas and biochemical analyzer, and confirms that the temperature control state of the blood gas and biochemical analyzer is in a normal state if the air duct temperature belongs to a preset air duct threshold temperature range. In this device, multiple ambient temperature filtering results and multiple heating sheet temperature filtering results can be obtained according to the ambient temperature and the heating sheet temperature corresponding to multiple time points respectively. As long as each heating sheet temperature filtering result meets the heating sheet threshold temperature under the corresponding ambient temperature filtering result, and the air duct temperature corresponding to the current time also meets the air duct threshold temperature range, it can ensure that the temperature control state of the blood gas and biochemical analyzer is in a normal state, thereby improving the accuracy of subsequent measurement data.

[0181] Further, the device further includes an air duct threshold temperature range acquisition module. The air duct threshold temperature range is acquired through the air duct threshold temperature range acquisition module. The air duct threshold temperature range acquisition module is configured to: acquire the current ambient temperature corresponding to the current time, and acquire the air duct threshold temperature range corresponding to the current ambient temperature from a preset second temperature relationship table, where the second temperature relationship table includes the air duct threshold temperature ranges corresponding to multiple ambient temperatures respectively.

[0182] Further, the first determination module 101 is further configured to: perform filtering processing on the obtained multiple ambient temperatures to obtain multiple ambient temperature filtering results; perform filtering processing on the obtained multiple heating sheet temperatures to obtain multiple heating sheet temperature filtering results.

[0183] The temperature anomaly determination device of the blood gas biochemical analyzer provided by the embodiments of the present invention has the same implementation principle and the same technical effects as those of the foregoing embodiments of the temperature anomaly determination method of the blood gas biochemical analyzer. For the sake of brief description, for the parts not mentioned in the embodiments of the temperature anomaly determination device of the blood gas biochemical analyzer, reference may be made to the corresponding contents in the foregoing embodiments of the temperature anomaly determination method of the blood gas biochemical analyzer.

[0184] The embodiments of the present invention provide a data correction device for a blood gas biochemical analyzer. The test card of the blood gas biochemical analyzer corresponds to multiple electrodes; as Figure 11 shown, the device includes:

[0185] A second determination module 110, configured to, for each electrode when it is confirmed that the temperature control state of the blood gas biochemical analyzer is in a normal state, determine the electrode temperature of the electrode according to the current ambient temperature and / or the current heating sheet temperature; wherein, the method described in any one of the foregoing is used to confirm whether the temperature control state of the blood gas biochemical analyzer is in a normal state; an excitation module 111, configured to apply an excitation signal to the sample to be tested to obtain a response signal; a calculation module 112, configured to calculate, according to the response signal and a preset first mathematical model, a component test result of a specified component in the sample to be tested at a standard electrode temperature; wherein, the first mathematical model is a mathematical model determined based on the standard electrode temperature; a correction module 113, configured to, if the electrode temperature is different from the standard electrode temperature, perform compensation correction on the component test result according to a preset second mathematical model to obtain a component correction result of the specified component at the electrode temperature; a third determination module 114, configured to, if the electrode temperature is the same as the standard electrode temperature, determine the component test result as the component correction result.

[0186] The above data correction device for a blood gas and biochemical analyzer, when it is confirmed that the temperature control state of the blood gas and biochemical analyzer is in a normal state, for each electrode, determines the electrode temperature of the electrode according to the current ambient temperature and / or the current heating sheet temperature; applies an excitation signal to the sample to be tested to obtain a response signal; calculates, according to the response signal and a preset first mathematical model, the component test result of a specified component in the sample to be tested at the standard electrode temperature; wherein, the first mathematical model is a mathematical model determined based on the standard electrode temperature; if the electrode temperature is different from the standard electrode temperature, compensates and corrects the component test result according to a preset second mathematical model to obtain the component correction result of the specified component at the electrode temperature; if the electrode temperature is the same as the standard electrode temperature, determines the component test result as the component correction result. In this device, on the premise that it is confirmed that the temperature control state of the blood gas and biochemical analyzer is in a normal state, the component test result of a specified component in the sample to be tested can be determined according to the first mathematical model, and by comparing the electrode temperature with the standard electrode temperature, the component test result is corrected to obtain the corresponding component correction result, ensuring that the component correction result is closer to the actual true value and improving the accuracy of data measurement.

[0187] Further, the response signal obtained by applying an excitation signal to the sample to be tested is an impedance modulus value, and the device further includes an impedance modulus value acquisition module, and the impedance modulus value acquisition module is used for: applying an excitation signal to the sample to be tested to obtain an impedance spectrum; determining a complex function based on the impedance spectrum; calculating the impedance modulus value according to the imaginary part and the real part of the complex function.

[0188] Further, the first mathematical model is as follows:

[0189] C M-pre =k*Z+b;

[0190] The second mathematical model is as follows:

[0191] C M = ;

[0192] Wherein, C M-pre is the component test result of the specified component M in the sample to be tested at the standard electrode temperature calculated; both k and b are coefficients; Z is the impedance modulus value; C M is the component correction result of the specified component M at the electrode temperature; T is the electrode temperature; GR M is the average relative change value.

[0193] Further, the device further includes a first mathematical model establishment module, and the first mathematical model establishment module is configured to: obtain test liquid samples with different pre-configured concentration gradients, and measure the impedance modulus values corresponding to the test liquid samples at different concentration gradients through a blood gas and biochemical analyzer; wherein, the blood gas and biochemical analyzer is located in a constant temperature and humidity chamber, and the temperature of the constant temperature and humidity chamber is set to make the electrode temperature reach the standard electrode temperature; perform linear fitting on the concentration and impedance modulus value of the test liquid sample to obtain a first mathematical model at the standard electrode temperature.

[0194] Further, the device further includes a second mathematical model establishment module, and the second mathematical model establishment module is configured to: establish multiple temperature intervals based on the standard electrode temperature; calculate the standard sample concentration value of the test liquid sample through the first mathematical model at the standard electrode temperature; calculate the component test results corresponding to the test liquid samples with the same concentration at the end point temperatures of the temperature intervals according to the first mathematical model; calculate the deviation results between the component test results and the standard sample concentration value; calculate the difference between the electrode temperature and the standard electrode temperature to obtain a difference result; calculate the ratio of the deviation result to the difference result to obtain an average relative change value; obtain a second mathematical model based on the average relative change value, the electrode temperature, and the standard electrode temperature to perform compensation and correction on the component test results to obtain the component correction result of the specified component at the electrode temperature.

[0195] Further, the second determination module 110 is further configured to: for each electrode, if the electrode is located outside the test card, calculate the electrode temperature of the electrode based on the current ambient temperature and a preset first fitting relationship.

[0196] Further, the specified component is HCT.

[0197] The data correction device of the blood gas and biochemical analyzer provided by the embodiments of the present invention has the same implementation principle and the same technical effects as those of the foregoing embodiments of the data correction method of the blood gas and biochemical analyzer. For the sake of brief description, for the parts not mentioned in the embodiments of the data correction device of the blood gas and biochemical analyzer, reference may be made to the corresponding content in the foregoing embodiments of the data correction method of the blood gas and biochemical analyzer.

[0198] Embodiments of the present invention further provide an electronic device. Refer to Figure 12 As shown, the electronic device includes a processor 130 and a memory 131. The memory 131 stores machine-executable instructions that can be executed by the processor 130, and the processor 130 executes the machine-executable instructions to implement the above-mentioned temperature anomaly judgment method or data correction method of the blood gas and biochemical analyzer.

[0199] Further, Figure 12The electronic device shown also includes a bus 132 and a communication interface 133. The processor 130, the communication interface 133, and the memory 131 are connected through the bus 132. Among them, the memory 131 may include high-speed random access memory (RAM, Random Access Memory), and may also include non-volatile memory, such as at least one disk memory. Through at least one communication interface 133 (which can be wired or wireless), a communication connection is realized between this system network element and at least one other network element. The Internet, wide area network, local area network, metropolitan area network, etc. can be used. The bus 132 can be an ISA bus, a PCI bus, an EISA bus, etc. The bus can be divided into an address bus, a data bus, a control bus, etc. For the sake of convenience of representation, Figure 12 only a bidirectional arrow is used in the figure, but it does not mean that there is only one bus or one type of bus.

[0200] The processor 130 may be an integrated circuit chip with signal processing capabilities. In the implementation process, each step of the above method can be completed by the integrated logic circuit in the hardware of the processor 130 or by instructions in software form. The above-mentioned processor 130 can be a general-purpose processor, including a central processing unit (CPU, Central Processing Unit for short), a network processor (NP, Network Processor for short), etc.; it can also be a digital signal processor (DSP, Digital Signal Processor for short), an application-specific integrated circuit (ASIC, Application Specific Integrated Circuit for short), a field-programmable gate array (FPGA, Field-Programmable Gate Array for short), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components. It can implement or execute the various methods, steps, and logic block diagrams disclosed in the embodiments of the present invention. The general-purpose processor can be a microprocessor or the processor can also be any conventional processor, etc. The steps of the method disclosed in combination with the embodiments of the present invention can be directly embodied as being executed and completed by a hardware decoding processor, or by a combination of hardware and software modules in the decoding processor. The software module can be located in a mature storage medium in the art such as random access memory, flash memory, read-only memory, programmable read-only memory, or electrically erasable programmable memory, registers, etc. This storage medium is located in the memory 131, and the processor 130 reads the information in the memory 131 and combines its hardware to complete the steps of the method in the foregoing embodiments.

[0201] An embodiment of the present invention further provides a machine-readable storage medium. The machine-readable storage medium stores machine-executable instructions. When the machine-executable instructions are called and executed by a processor, the machine-executable instructions prompt the processor to implement the above-mentioned temperature anomaly judgment method and data correction method of the blood gas biochemical analyzer. For the specific implementation, reference can be made to the method embodiments and will not be elaborated here.

[0202] A computer program product of the temperature anomaly judgment method and data correction method of the blood gas biochemical analyzer provided by an embodiment of the present invention includes a computer-readable storage medium storing program codes. The instructions included in the program codes can be used to execute the methods described in the foregoing method embodiments. For the specific implementation, reference can be made to the method embodiments and will not be elaborated here.

[0203] If the above functions are implemented in the form of software function units and sold or used as independent products, they can be stored in a computer-readable storage medium. Based on such an understanding, the technical solution of the present invention, in essence, or the part that contributes to the prior art, or a part of the technical solution, can be embodied in the form of a software product. The computer software product is stored in a storage medium and includes several instructions for causing a computer device (which may be a personal computer, a server, or a network device, etc.) to execute all or part of the steps of the methods described in various embodiments of the present invention. The foregoing storage medium includes: various media such as USB flash drives, mobile hard disks, read-only memories (ROM, Read-Only Memory), random access memories (RAM, Random Access Memory), magnetic disks, or optical discs that can store program codes.

[0204] Finally, it should be noted that: the above embodiments are only used to illustrate the technical solutions of the present invention and are not intended to limit them; although the present invention has been described in detail with reference to the foregoing embodiments, those of ordinary skill in the art should understand that they can still modify the technical solutions described in the foregoing embodiments, or perform equivalent replacements on some or all of the technical features; and these modifications or replacements do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of various embodiments of the present invention.

Claims

1. A method for judging temperature abnormality of a blood gas biochemical analyzer, characterized in that, A heating sheet is provided at a preset position of the test card of the blood gas analyzer; The heating sheet is used to heat the test card; The method includes: Obtaining the ambient temperature and the heating sheet temperature corresponding to multiple time points respectively within a specified time period determined based on the current time; wherein, the ambient temperature is collected by a vent temperature probe located on the surface of the blood gas analyzer; Determining multiple ambient temperature filtering results based on the multiple ambient temperatures; determining multiple heating sheet temperature filtering results based on the multiple heating sheet temperatures; Obtaining the heating sheet threshold temperature corresponding to each ambient temperature filtering result from a preset first temperature relationship table; wherein, the first temperature relationship table includes the heating sheet threshold temperatures corresponding to multiple ambient temperatures, and each heating sheet threshold temperature in the first temperature relationship table is a temperature value or a temperature range; If each current heating sheet temperature filtering result meets the corresponding heating sheet threshold temperature, obtaining the duct temperature corresponding to the current time; wherein, the duct temperature is used to represent the temperature of the internal duct of the blood gas analyzer; the duct temperature is collected by a channel temperature probe suspended above the test card insertion position of the blood gas analyzer and located in the ventilated duct of the blood gas analyzer, at the central position of the blood gas analyzer; If the duct temperature belongs to a preset duct threshold temperature range, confirming that the temperature control state of the blood gas analyzer is in a normal state.

2. The method according to claim 1, characterized in that, The duct threshold temperature range is obtained by the following method: Obtaining the current ambient temperature corresponding to the current time; Obtaining the duct threshold temperature range corresponding to the current ambient temperature from a preset second temperature relationship table; wherein, the second temperature relationship table includes the duct threshold temperature ranges corresponding to multiple ambient temperatures.

3. The method according to claim 1, characterized in that, The steps of determining multiple ambient temperature filtering results based on the multiple ambient temperatures and determining multiple heating sheet temperature filtering results based on the multiple heating sheet temperatures include: Performing filtering processing on the obtained multiple ambient temperatures to obtain multiple ambient temperature filtering results; performing filtering processing on the obtained multiple heating sheet temperatures to obtain multiple heating sheet temperature filtering results.

4. A method for data calibration of a blood gas and biochemical analyzer, characterized in that, The test card of the blood gas analyzer corresponds to multiple types of electrodes; The method includes: When it is confirmed that the temperature control state of the blood gas analyzer is in a normal state, for each type of electrode, determining the electrode temperature of the electrode according to the current ambient temperature and / or the current heating sheet temperature; wherein, the method described in any one of claims 1-3 is used to confirm whether the temperature control state of the blood gas analyzer is in a normal state; Applying an excitation signal to the sample to be tested to obtain a response signal; Calculating, according to the response signal and a preset first mathematical model, the component test result of a specified component in the sample to be tested at the standard electrode temperature; wherein, the first mathematical model is a mathematical model determined based on the standard electrode temperature; If the electrode temperature is different from the standard electrode temperature, compensate and correct the component test result according to a preset second mathematical model to obtain the component correction result of the specified component at the electrode temperature; If the electrode temperature is the same as the standard electrode temperature, determine the component test result as the component correction result; The first mathematical model is as follows: C M-pre = k * Z + b; Among them, C M-pre is the component test result of the specified component M in the sample to be measured at the standard electrode temperature obtained by calculation; both k and b are coefficients; Z is the impedance modulus; The method for establishing the second mathematical model includes: Establish multiple temperature interval segments based on the standard electrode temperature; Calculate the standard sample concentration value of the test liquid sample through the first mathematical model at the standard electrode temperature; According to the first mathematical model, calculate the component test results corresponding to the test liquid samples with the same concentration at the end point temperatures of the temperature interval segments; Calculate the deviation result between the component test result and the standard sample concentration value; Calculate the difference between the electrode temperature and the standard electrode temperature to obtain a difference result; Calculate the ratio of the deviation result to the difference result to obtain an average relative change value; Based on the average relative change value, the electrode temperature, and the standard electrode temperature, obtain a second mathematical model to compensate and correct the component test result to obtain the component correction result of the specified component at the electrode temperature.

5. The method according to claim 4, characterized in that, Apply an excitation signal to the sample to be tested, and the obtained response signal is the impedance modulus value. The steps for obtaining the impedance modulus value include: Apply an excitation signal to the sample to be tested to obtain an impedance spectrum; Determine a complex function based on the impedance spectrum; Calculate the impedance modulus value according to the imaginary part and the real part of the complex function.

6. The method according to claim 4, wherein The method for establishing the first mathematical model includes: Obtain pre-configured test liquid samples with different concentration gradients, and measure the impedance modulus values corresponding to the test liquid samples at different concentration gradients through a blood gas biochemical analyzer; wherein, the blood gas biochemical analyzer is located in a constant temperature and humidity chamber, and the temperature of the constant temperature and humidity chamber is set to make the electrode temperature reach the standard electrode temperature; Use linear fitting to fit the concentration of the test liquid sample and the impedance modulus value to obtain the first mathematical model at the standard electrode temperature.

7. The method according to claim 4, wherein For each electrode, the steps for determining the electrode temperature of the electrode according to the current ambient temperature and / or the current heating sheet temperature include: For each electrode, if the electrode is located outside the test card, calculate the electrode temperature of the electrode based on the current ambient temperature and a preset first fitting relationship.

8. The method according to claim 4, wherein The specified component is HCT.

9. A temperature abnormality determination device for a blood gas biochemical analyzer, characterized in that, A heating sheet is provided at a preset position of the test card of the blood gas biochemical analyzer; the heating sheet is used to heat the test card; the device includes: A first acquisition module, configured to acquire the ambient temperature and the heating sheet temperature corresponding to multiple time points respectively within a specified time period determined based on the current time; wherein, the ambient temperature is acquired through a ventilation port temperature probe, and the ventilation port temperature probe is located on the surface of the blood gas biochemical analyzer; A first determination module, configured to determine multiple ambient temperature filtering results based on multiple ambient temperatures; and determine multiple heating sheet temperature filtering results based on multiple heating sheet temperatures; A second acquisition module, configured to acquire the threshold temperature of the heating sheet corresponding to each ambient temperature filtering result from a preset first temperature relationship table; wherein, the first temperature relationship table includes the threshold temperatures of the heating sheet corresponding to multiple ambient temperatures respectively, and each of the threshold temperatures of the heating sheet in the first temperature relationship table is a temperature value or a temperature range; A third acquisition module, configured to acquire the air duct temperature corresponding to the current time if the current temperature filtering result of each heating sheet meets the corresponding threshold temperature of the heating sheet; wherein, the air duct temperature is used to represent the temperature of the internal air duct of the blood gas analyzer; the air duct temperature is collected by a channel temperature probe, the channel temperature probe is suspended above the test card insertion position of the blood gas analyzer, and is located in the ventilated air duct of the blood gas analyzer, and is at the central position of the blood gas analyzer; A confirmation module, configured to confirm that the temperature control state of the blood gas analyzer is in a normal state if the air duct temperature belongs to a preset air duct threshold temperature range.

10. A data calibration device for a blood gas biochemical analyzer, characterized in that, The test card of the blood gas analyzer corresponds to multiple electrodes; the device includes: A second determination module, configured to determine the electrode temperature of each electrode according to the current ambient temperature and / or the current heating sheet temperature when it is confirmed that the temperature control state of the blood gas analyzer is in a normal state; wherein, the method described in any one of claims 1-3 is used to confirm whether the temperature control state of the blood gas analyzer is in a normal state; An excitation module, configured to apply an excitation signal to the sample to be tested to obtain a response signal; A calculation module, configured to calculate the component test result of the specified component in the sample to be tested at the standard electrode temperature according to the response signal and a preset first mathematical model; wherein, the first mathematical model is a mathematical model determined based on the standard electrode temperature; A correction module, configured to, if the electrode temperature is different from the standard electrode temperature, compensate and correct the component test result according to a preset second mathematical model to obtain the component correction result of the specified component at the electrode temperature; A third determination module, configured to, if the electrode temperature is the same as the standard electrode temperature, determine the component test result as the component correction result; The first mathematical model is as follows: C M-pre = k * Z + b; where C M-pre is the test result of the specified component M in the sample to be tested at the standard electrode temperature; both k and b are coefficients; Z is the impedance modulus value; The device further includes a second mathematical model establishment module, and the second mathematical model establishment module is configured to: Establish multiple temperature interval segments based on the standard electrode temperature; Calculate the standard sample concentration value of the test liquid sample through the first mathematical model at the standard electrode temperature; Calculate the component test results corresponding to the test liquid samples with the same concentration at the endpoint temperatures of the temperature interval segments according to the first mathematical model; Calculate the deviation result between the component test result and the standard sample concentration value; Calculate the difference between the electrode temperature and the standard electrode temperature to obtain a difference result; Calculate the ratio of the deviation result to the difference result to obtain an average relative change value; Based on the average relative change value, the electrode temperature, and the standard electrode temperature, a second mathematical model is obtained to compensate and correct the component test result, and a component correction result of the specified component at the electrode temperature is obtained.

11. An electronic device, characterized in that, It includes a processor and a memory. The memory stores machine-executable instructions that can be executed by the processor. The processor executes the machine-executable instructions to implement the temperature anomaly determination method of the blood gas biochemical analyzer according to any one of claims 1-3, or the data correction method of the blood gas biochemical analyzer according to any one of claims 4-8.

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