A method and device for generating simulated human electrocardiogram signals

Abstract

This application relates to the technical field of hemodynamic simulation, and in particular to a method and device for simulating human electrocardiogram signals. The method for simulating human electrocardiogram signals includes the steps of: obtaining a hemodynamic parameter detection instruction, generating an electrocardiogram simulation signal based on the hemodynamic detection instruction, and inputting the electrocardiogram simulation signal into an impedance terminal; generating an impedance adjustment instruction according to the state of the adjustment module, and adjusting the impedance value output by the impedance terminal based on the impedance adjustment instruction; inputting the impedance value into the electrocardiogram simulation signal to obtain a blood flow simulation electrocardiogram signal; outputting the blood flow simulation electrocardiogram signal to a hemodynamic detection terminal, and the hemodynamic detection terminal generates a blood flow parameter detection report based on the blood flow simulation electrocardiogram signal. This application has the effect of more accurately simulating the impedance generated when human blood flows, providing different simulated impedance data, and improving the accuracy of hemodynamic parameter measurement.

Description

Technical Field

[0001] This application relates to the technical field of hemodynamic simulation, and particularly to a method and device for simulating the generation of human electrocardiogram signals. Background Art

[0002] Cardiovascular diseases have become one of the major diseases threatening human life and health, thus attracting more and more attention. How to scientifically detect cardiovascular diseases at an early stage has become a serious problem. Hemodynamic parameters are an important basis for studying cardiovascular function. At present, the methods for detecting blood vessels generally use non-invasive hemodynamic parameter measurement methods, mainly including two categories: ultrasonic Doppler measurement and bioimpedance measurement.

[0003] However, the existing non-invasive hemodynamic parameter measurement methods do not consider the influence of different impedances generated by human blood flow on the measurement results. Different impedance values will be generated by human blood flow, which will interfere with the collected electrocardiogram signals, and then lead to the fact that the measurement results of hemodynamic parameters do not accurately fit the blood flow situation of the human body, resulting in a decrease in the accuracy of the measurement results of hemodynamic parameters. Therefore, there is still room for improvement. Summary of the Invention

[0004] In order to more accurately simulate the impedance generated when human blood flows, provide different simulated impedance data, and improve the accuracy of hemodynamic parameter measurement, this application provides a method and device for simulating the generation of human electrocardiogram signals.

[0005] In the first aspect, this application provides a method for simulating the generation of human electrocardiogram signals, adopting the following technical solutions:

[0006] A method for simulating the generation of human electrocardiogram signals, the method for simulating the generation of human electrocardiogram signals includes the steps of:

[0007] The main control module generates electrocardiogram simulation signal parameters, inputs the electrocardiogram simulation signal parameters into the electrocardiogram simulation signal module, and the electrocardiogram simulation signal module outputs an electrocardiogram simulation signal to the impedance network;

[0008] Generate an impedance adjustment instruction according to the state of the adjustment module, and adjust the impedance value output by the impedance terminal based on the impedance adjustment instruction;

[0009] Input the impedance value into the electrocardiogram simulation signal to obtain a blood flow simulation electrocardiogram signal;

[0010] Output the blood flow simulation electrocardiogram signal to the hemodynamic detection terminal, and generate a hemodynamic parameter detection report based on the blood flow simulation electrocardiogram signal.

[0011] By adopting the above technical solution, during the non-invasive hemodynamic parameter measurement process, the tester starts the non-invasive hemodynamic parameter measurement device to generate a hemodynamic parameter detection instruction. The electrodes on the non-invasive hemodynamic parameter measurement device collect the bioelectrical signals generated by the human heartbeat, generate an electrocardiogram analog signal according to the bioelectrical signals. Before inputting the electrocardiogram analog signal into the hemodynamic detection terminal, the electrocardiogram analog signal is first input into the impedance terminal. The impedance terminal adjusts to generate different impedance values to simulate the impedance change situation generated by the human blood flow. The electrocardiogram analog signal is divided by using different impedance values set in the impedance terminal to obtain a blood flow simulated electrocardiogram signal, which can make the electrocardiogram analog signal input into the hemodynamic detection terminal more conform to the human body simulation situation, and further make the detection result of the obtained blood flow parameter more accurate and more in line with the actual human body situation. After receiving the blood flow simulated electrocardiogram signal, the blood flow parameter detection terminal generates a blood flow parameter detection report.

[0012] In a preferred example of the present application, it can be further configured that: generating an impedance adjustment instruction according to the state of the adjustment module, and adjusting the impedance value output by the impedance terminal based on the impedance adjustment instruction, specifically including:

[0013] Inputting the impedance adjustment instruction into the impedance terminal, and the impedance terminal accesses different resistors according to the impedance adjustment instruction;

[0014] Based on the parallel connection of the different resistors, different resistance values are generated, and the impedance terminal generates different impedance values based on the different resistance values.

[0015] By adopting the above technical solution, when the impedance terminal receives the impedance adjustment instruction, several resistors connected in parallel are electrically connected in the impedance terminal. The impedance terminal will control the on-off situation of the circuits of different resistors according to the impedance adjustment instruction. By connecting different numbers of resistors in parallel, the resistance values in the impedance terminal are different, and thus the impedance terminal can generate different impedance values to realize the function of simulating different impedance values generated by the human blood flow.

[0016] In a preferred example of the present application, it can be further configured that: before obtaining the hemodynamic parameter detection instruction, generating an electrocardiogram analog signal based on the hemodynamic detection instruction, and inputting the electrocardiogram analog signal into the impedance terminal, it further includes:

[0017] Obtaining bioelectrical signals based on the hemodynamic parameter detection instruction, and performing rejection filtering processing on the bioelectrical signals;

[0018] Taking the bioelectrical signal after rejection filtering as the electrocardiogram analog signal.

[0019] By adopting the above technical solution, the human bioelectromyogram signal is collected through the electrode, and the collected bioelectromyogram signal is subjected to rejection filtering processing, which can eliminate the interference signal from collecting the bioelectromyogram signal. The filtering processing makes the transmission of the bioelectromyogram signal more stable. The bioelectromyogram signal after rejection filtering processing is used as the electrocardiogram analog signal, and tests are carried out with this electrocardiogram analog signal to achieve the function of improving the accuracy of blood flow dynamic parameter measurement.

[0020] In a second aspect, the present application provides a device for generating an analog human electrocardiogram signal, adopting the following technical solution:

[0021] A device for generating an analog human electrocardiogram signal includes a main control module, an electrocardiogram analog signal module, an adjustment module, a switch module, and an impedance module. The input end of the electrocardiogram analog signal module is coupled to the main control module. The output end of the electrocardiogram analog signal module is connected in series with the impedance module and then coupled to the blood flow dynamics detection terminal. The adjustment module is electrically connected to the main control module. The adjustment module is used to output an impedance adjustment signal to the main control module. The input end of the switch module is coupled to the main control module. The output end of the switch module is connected in series with the impedance module. The main control module is used to output a control signal to the switch module after receiving the impedance adjustment signal. The switch module is used to control the on / off of the impedance module according to the control signal. The impedance module outputs different impedance values according to the on / off situation.

[0022] By adopting the above technical solution, the main control module receives the bioelectromyogram signal and outputs an analog signal to the electrocardiogram analog signal module. The electrocardiogram analog signal module forms an electrocardiogram analog signal after receiving the analog signal and outputs it to the impedance module. Medical staff generate an impedance adjustment signal through the adjustment module and output it to the main control module. The main control module outputs a control signal to the switch module after receiving the impedance adjustment signal. The switch module controls the on / off situation of each sub-circuit in the impedance module after receiving the control signal. The impedance module generates different impedance values according to the on / off situation. The electrocardiogram analog signal output by the electrocardiogram analog signal module is subjected to voltage division processing with different impedance values and then output to the blood flow dynamics detection terminal to complete the analog measurement of blood flow dynamic parameters. By using the main control module to control the on / off situation of the switch module, the impedance module generates different impedance values, and thus can accurately simulate the impedance generated when human blood flows, providing different analog impedance data, thereby improving the accuracy of the blood flow dynamic parameter detection result.

[0023] Preferably, it further includes a power conversion module. The input end of the power conversion module is coupled to the power supply. The output end of the power conversion module is respectively coupled to the main control module, the electrocardiogram analog signal module, the adjustment module, and the switch module. The power conversion module is used to provide a power supply voltage for the device for generating an analog human electrocardiogram signal.

[0024] By adopting the above technical solution, a power conversion module is provided. The power conversion module converts the power supply voltage into working voltages suitable for the main control module, the electrocardiogram analog signal module, the adjustment module, and the switch module, thereby realizing the power supply function for the analog human electrocardiogram signal generating device.

[0025] Preferably, the main control module includes a main control chip U3. The main control chip U3 includes an adjustment signal input terminal, a control signal output terminal, and an analog signal output terminal. The adjustment signal input terminal of the main control chip U3 is coupled to the adjustment module to input an impedance adjustment signal. The analog signal output terminal of the main control chip U3 is coupled to the electrocardiogram analog signal module to output an analog signal to the electrocardiogram analog signal module. The control signal output terminal of the main control chip U3 is coupled to the switch module to output a control signal to the switch module. The power supply terminal of the main control chip U3 is coupled to the power conversion module to input the working voltage.

[0026] By adopting the above technical solution, the main control chip U3 inputs the working voltage through the power supply terminal, the main control chip U3 is powered on and works. The main control chip U3 outputs an analog signal to the electrocardiogram analog signal module through the analog signal output terminal to be converted into an analog signal. The main control chip U3 inputs an impedance adjustment signal through the adjustment signal input terminal, and outputs a control signal to the switch module through the control signal output terminal according to the impedance adjustment signal, thereby realizing the function of controlling the on / off of the adjustment switch module, and further realizing the function of controlling the generation of different impedance values.

[0027] Preferably, the electrocardiogram analog signal module includes an analog chip U1. The analog chip U1 includes an analog signal input terminal and an output terminal. The analog signal input terminal of the analog chip U1 is coupled to the analog signal output terminal of the main control chip U3 to receive an analog signal. The output terminal of the analog chip U1 is coupled to the blood flow dynamics detection terminal in series with the impedance module. The power supply terminal of the analog chip U1 is coupled to the power conversion module in series with a filter circuit.

[0028] By adopting the above technical solution, the analog chip U1 inputs an analog signal through the analog signal input terminal, and filters the power supply signal through the filter circuit on the power supply terminal to output a clean electrocardiogram analog signal, thereby making the output electrocardiogram analog signal more accurate. The electrocardiogram analog signal is output to the impedance module through the output terminal, realizing the function of providing an electrocardiogram analog signal for the blood flow dynamics detection terminal.

[0029] Preferably, the switch module includes a plurality of optocoupler chips. The input terminal of each optocoupler chip is coupled to the control signal output terminal of the main control chip U3 to receive a control signal. The output terminal of each optocoupler chip is coupled to the impedance module to output a switch signal to the impedance module.

[0030] By adopting the above technical solution, when the switch module receives a control signal, it controls one or more optoelectronic coupling chips to conduct, and outputs a switch signal to the impedance module, realizing the function of controlling the power on and off of the impedance module.

[0031] Preferably, the impedance module includes a parallel resistor network and two resistors. The parallel resistor bridge includes a plurality of resistors connected in parallel with each other. The parallel resistor network and the two resistors are connected in series with each other. One end of the parallel resistor bridge is respectively coupled to the output end of the optoelectronic coupling chip and the output end of the analog chip U1, and the other end of the parallel resistor bridge is coupled to the hemodynamic detection terminal.

[0032] By adopting the above technical solution, after the impedance module receives the switch signal, the resistance value of the parallel resistor network changes with the on / off state of the optoelectronic coupling chip. Furthermore, the impedance module can generate different impedance values to divide the voltage of the electrocardiogram analog signal, realizing the function of simulating the impedance generated when human blood flows and providing different analog impedance data.

[0033] In summary, the present application includes at least one of the following beneficial technical effects:

[0034] 1. By using different impedance values set in the impedance terminal to divide the voltage of the electrocardiogram analog signal, a blood flow-simulated electrocardiogram signal is obtained, which can make the electrocardiogram analog signal input to the hemodynamic detection terminal more conform to the human body simulation situation. Furthermore, the detection result of the blood flow parameter obtained is more accurate and more in line with the actual human body situation;

[0035] 2. A number of resistors connected in parallel are electrically connected in the impedance terminal. The impedance terminal controls the on / off state of the circuits of different resistors according to the impedance adjustment instruction. By connecting different numbers of resistors in parallel, the resistance values in the impedance terminal are different. Furthermore, the impedance terminal can generate different impedance values, realizing the function of simulating different impedance values generated by human blood flow;

[0036] 3. By performing rejection filtering on the electrocardiogram analog signal, the interference of the interference signal on the electrocardiogram analog signal can be eliminated. The filtering process makes the transmission of the electrocardiogram analog signal more stable. The electrocardiogram analog signal after the rejection filtering process is used as the output electrocardiogram analog signal, and the blood flow dynamic parameter measurement is tested with this electrocardiogram analog signal, realizing the function of improving the accuracy of the blood flow dynamic parameter measurement. BRIEF DESCRIPTION OF THE DRAWINGS

[0037] Figure 1 is a flowchart of an embodiment of a method for simulating a human electrocardiogram signal in the present application.

[0038] Figure 2 is a flowchart for implementing step S20 in an embodiment of a method for simulating a human electrocardiogram signal in the present application.

[0039] Figure 3 It is another implementation flowchart of an embodiment of a method for generating an analog human electrocardiogram (ECG) signal according to the present application.

[0040] Figure 4 It is a module structure diagram of an embodiment of an apparatus for generating an analog human electrocardiogram (ECG) signal according to the present application.

[0041] Figure 5 It is a circuit diagram of a power conversion module of an embodiment of an apparatus for generating an analog human electrocardiogram (ECG) signal according to the present application.

[0042] Figure 6 It is a circuit diagram of a main control module of an embodiment of an apparatus for generating an analog human electrocardiogram (ECG) signal according to the present application.

[0043] Figure 7 It is a circuit diagram of an ECG analog signal module of an embodiment of an apparatus for generating an analog human electrocardiogram (ECG) signal according to the present application.

[0044] Figure 8 It is a circuit diagram of a switch module of an embodiment of an apparatus for generating an analog human electrocardiogram (ECG) signal according to the present application.

[0045] Explanation of reference numerals: 1. Power conversion module; 2. Main control module; 3. ECG analog signal module; 4. Adjustment module; 5. Switch module; 6. Impedance module; 7. Hemodynamic detection terminal. Detailed implementation manners

[0046] In order to make the objectives, technical solutions and advantages of the present application clearer and more understandable, the following further Figure 1-8 describes the present application in detail with reference to the accompanying

[0047] In one embodiment, as Figure 1 shown, the present application discloses a method for generating an analog human electrocardiogram (ECG) signal, which specifically includes the following steps:

[0048] S10: Obtain a hemodynamic parameter detection instruction, generate an ECG analog signal based on the hemodynamic detection instruction, and input the ECG analog signal into an impedance terminal.

[0049] In this embodiment, the hemodynamic parameter detection instruction refers to a control instruction for measuring hemodynamic parameters, the ECG analog signal refers to an analog signal converted from a bioelectrical signal generated by a human heartbeat, and the impedance terminal refers to a terminal that provides an impedance value.

[0050] Specifically, a medical staff member starts a non-invasive hemodynamic parameter measurement device. The device generates a hemodynamic parameter measurement control instruction. The main control module on the device generates ECG analog signal parameters, which are converted into an ECG analog signal through the ECG analog signal module, and the ECG analog signal is input into an impedance terminal with a certain impedance value.

[0051] S20: Generate an impedance adjustment instruction according to the state of the adjustment module, and adjust the impedance value output by the impedance terminal based on the impedance adjustment instruction.

[0052] In this embodiment, the impedance adjustment instruction refers to a control instruction for adjusting the impedance value of the impedance terminal.

[0053] Specifically, medical staff generate a control instruction for adjusting the impedance value of the impedance terminal through a button. After the impedance terminal receives the control instruction for adjusting the impedance value, it adjusts to generate different impedance values, simulating the impedance change caused by the blood flow in the human body, and realizes the voltage division processing of the electrocardiogram analog signal by setting different impedance values in the impedance terminal.

[0054] S30: Input the impedance value into the electrocardiogram analog signal to obtain a blood flow simulation electrocardiogram signal.

[0055] In this embodiment, the blood flow simulation electrocardiogram signal refers to the electrocardiogram signal finally output when the impedance value of the human body changes due to the blood flow in the blood vessels, and the change of the impedance value of the human body affects the change of the electrocardiogram signal.

[0056] Specifically, the electrocardiogram analog signal is divided by different impedance values to correspondingly simulate the different impedance effects generated by the blood flow in the human body, obtaining an electrocardiogram signal that is more suitable for the human body simulation, realizing that the detection result of the blood flow parameter obtained is more accurate and more in line with the actual human situation.

[0057] S40: Output the blood flow simulation electrocardiogram signal to the blood flow dynamics detection terminal, and generate a blood flow parameter detection report based on the blood flow simulation electrocardiogram signal.

[0058] In this embodiment, the blood flow dynamics detection terminal refers to a terminal that uses an electrocardiogram analog signal for blood flow parameter analysis, and the blood flow parameter detection report refers to a parameter data report of the human cardiovascular system.

[0059] Specifically, the electrocardiogram analog signal divided by different impedance values is input into the blood flow dynamics detection terminal, and the blood flow parameters are analyzed using the electrocardiogram analog signal, and then a parameter data report simulating the human cardiovascular system is obtained. Medical staff compare and analyze the simulated blood flow parameter detection report with the human body measurement detection report to realize the pre-detection of the health status of the human cardiovascular system.

[0060] In this embodiment, during the non-invasive hemodynamic parameter measurement process, the tester activates the non-invasive hemodynamic parameter measurement device to generate a hemodynamic parameter detection instruction. The electrodes on the non-invasive hemodynamic parameter measurement device collect the analog electrocardiogram (ECG) signal output by the human ECG signal generating device. Before inputting the ECG analog signal into the hemodynamic detection terminal, the ECG analog signal is first input into the impedance terminal. The impedance terminal adjusts to generate different impedance values to simulate the impedance transformation situation generated by human blood flow. Using different impedance values set in the impedance terminal to perform voltage division processing on the ECG analog signal to obtain a blood flow simulated ECG signal, which can make the ECG analog signal input into the hemodynamic detection terminal more conform to the human simulation situation, thereby making the detection result of the obtained blood flow parameters more accurate and more in line with the actual human situation. After receiving the blood flow simulated ECG signal, the blood flow parameter detection terminal generates a blood flow parameter detection report, and the medical staff compares and analyzes according to the blood flow parameter detection report and the human blood flow parameter detection report, and then can pre-detect the health condition of the human cardiovascular system.

[0061] In one embodiment, as Figure 2 shown, in step S20, that is, generating an impedance adjustment instruction according to the ECG analog signal and adjusting the impedance value output by the impedance terminal based on the impedance adjustment instruction, specifically includes:

[0062] S21: Input the impedance adjustment instruction into the impedance terminal, and the impedance terminal accesses different resistors according to the impedance adjustment instruction.

[0063] Specifically, when the impedance terminal receives the impedance adjustment instruction, the on-off situation of the circuits controlling different resistors in the impedance terminal is controlled, and the number of resistors in the parallel connection is controlled to realize the function of controlling the resistance values of different parallel-connected resistors.

[0064] S22: Based on the parallel connection of the different resistors, different resistance values are generated, and the impedance terminal generates different impedance values based on the different resistance values.

[0065] In this embodiment, the impedance value refers to the impedance value generated by simulating human blood flow.

[0066] Specifically, when the impedance terminal receives the impedance adjustment instruction, there are several resistors connected in parallel in the impedance terminal. The impedance terminal will control the on-off situation of the circuits of different resistors according to the impedance adjustment instruction. By connecting different numbers of resistors in parallel, the resistance values in the impedance terminal are different, and thus the impedance terminal can generate different impedance values to realize the function of simulating different impedance values generated by human blood flow.

[0067] In one embodiment, as Figure 3As shown, before step S10, that is, before obtaining a blood hemodynamic parameter detection instruction, generating an electrocardiogram (ECG) simulation signal based on the blood hemodynamic detection instruction, and inputting the ECG simulation signal into an impedance terminal, a method for simulating a human ECG signal further includes the following steps:

[0068] S101: Obtain a simulated bioelectrical muscle signal based on the blood hemodynamic parameter detection instruction, and perform rejection filtering processing on the simulated bioelectrical muscle signal.

[0069] In this embodiment, the rejection filtering process refers to filtering and removing interference signals in the simulated bioelectrical muscle signal.

[0070] Specifically, in the collected simulated bioelectrical muscle signal, there will be bioelectrical muscle signals that do not belong to the simulated cardiovascular system, and there will also be the influence of electromagnetic interference signals on the simulated bioelectrical muscle signal. By performing rejection filtering processing on the simulated bioelectrical muscle signal, the interference signals in the simulated bioelectrical muscle signal will be filtered and removed, thereby obtaining a simulated bioelectrical muscle signal with high accuracy and improving the accuracy of detection. S102: Use the simulated bioelectrical muscle signal after rejection filtering as the ECG simulation signal.

[0071] Specifically, by performing rejection filtering processing on the simulated bioelectrical muscle signal to eliminate the influence of interference signals on the simulated bioelectrical muscle signal, the filtering process makes the transmission of the simulated bioelectrical muscle signal more stable. Using the simulated bioelectrical muscle signal after rejection filtering as the ECG simulation signal and testing with this ECG simulation signal can achieve the function of improving the accuracy of blood hemodynamic parameter measurement.

[0072] In one embodiment, the present application also discloses a device for simulating a human ECG signal. This device for simulating a human ECG signal corresponds one-to-one with the method for simulating a human ECG signal in the above embodiment, as Figure 4 shown, a device for simulating a human ECG signal includes a power supply module, a main control module 2, an ECG simulation signal module 3, an adjustment module 4, a switch module 5, and an impedance module 6.

[0073] The output terminals of the power conversion module 1 are respectively coupled to the main control module 2, the ECG simulation signal module 3, the adjustment module 4, and the switch module 5. The power conversion module 1 is used to convert the power supply voltage into a working voltage suitable for the operation of the main control module 2, the ECG simulation signal module 3, the adjustment module 4, and the switch module 5. The input terminal of the ECG simulation signal module 3 is coupled to the main control module 2 to receive the simulation signal. The adjustment module 4 is coupled to the main control module 2, and the adjustment module 4 is used to generate an impedance adjustment signal and output it to the main control module 2. The input terminal of the switch module 5 is coupled to the main control module 2, the output terminal of the switch module 5 is connected in series with the impedance module 6, and the output terminal of the ECG simulation signal module 3 is connected in series with the impedance module 6 and then coupled to the blood hemodynamic detection terminal 7.

[0074] Specifically, the power conversion module 1 converts the power supply voltage into the operating voltages for the main control module 2, the electrocardiogram analog signal module 3, the adjustment module 4, and the switch module 5. The main control module 2 converts the bioelectrical muscle signals collected by the electrodes into analog signals and outputs them to the electrocardiogram analog signal module 3. After receiving the analog signals, the electrocardiogram analog signal module 3 forms electrocardiogram analog signals. Medical staff generate impedance adjustment signals through the adjustment module 4 and output them to the main control module 2. After receiving the impedance adjustment signals, the main control module 2 generates control signals and outputs them to the switch module 5. The switch module 5 outputs switch signals to the impedance module 6 according to the control signals to control the on / off states of the respective resistor sub-circuits in the impedance module 6. The impedance module 6 generates different resistance values based on the on / off states of its internal resistor sub-circuits, forms different impedance values based on the different resistance values, and then simulates the different impedances generated during human blood flow. The electrocardiogram analog signal module 3 performs voltage division processing on the electrocardiogram analog signals through the impedance module 6 and outputs the processed electrocardiogram analog signals to the blood flow dynamics detection terminal 7, completing the blood flow dynamics parameter simulation test process.

[0075] Refer to Figure 5 As shown in the figure, the power conversion module 1 includes a conversion chip U2. The conversion chip U2 has eight pins. The eighth pin of the conversion chip U2 is coupled to the 9V power supply voltage. The eighth pin of the conversion chip U2 is also coupled with a twenty-eighth capacitor C28. The other end of the twenty-eighth capacitor C28 is grounded. The two ends of the twenty-eighth capacitor C are in parallel with a twenty-ninth capacitor C29. The eighth pin of the conversion chip U2 is also coupled with a fifth resistor R5. The other end of the fifth resistor R5 is coupled with a sixth resistor R6. The other end of the sixth resistor R6 is grounded. The two ends of the sixth resistor R6 are in parallel with a first capacitor C1. The fifth pin of the conversion chip U2 is coupled to the fourth pin and then grounded. The third pin of the conversion chip U2 is coupled to the connection node of the sixth resistor R6 and the fifth resistor R5. The seventh pin of the conversion chip U2 is coupled to the main control module 2. The first pin of the conversion chip U1 is coupled to the second pin. The second pin of the conversion chip U2 is coupled with a seventh capacitor C7. The other end of the seventh capacitor C7 is grounded. The two ends of the seventh capacitor C7 are in parallel with an eighth capacitor C8. The connection node of the eighth capacitor C8 and the seventh capacitor C7 is coupled with a twelfth resistor R12. The other end of the twelfth resistor R12 is coupled with a ninth capacitor C9. The other end of the ninth capacitor C9 is grounded. The connection node of the twelfth resistor R12 and the eighth capacitor C8 is coupled with a seventeenth TVS tube D17. The other end of the seventeenth TVS tube D17 is grounded. The connection node of the twelfth resistor R12 and the seventeenth TVS tube D17 outputs a 5V DC voltage for supplying power to other circuits in the device.

[0076] Specifically, the conversion chip converts the 9V DC voltage into a 5V DC voltage to supply power to other module circuits in the device. The seventeenth TVS tube D17 absorbs the transient pulse impact generated by external interference in the power conversion module 1 circuit, protecting the voltage conversion chip U2 from damage by transient pulses and improving the stability of the converted output voltage.

[0077] Refer to Figure 6 , the main control module 2 includes a main control chip U3, the adjustment module 4 includes a switch S1, an eighth resistor R8, and a ninth resistor R9. One end of the switch S1 is connected in series with a seventh resistor R7 and then coupled to the 5V DC voltage. The other end of the switch S1 is grounded. Both ends of the switch S1 are connected in parallel with a seventh TVS tube D7. One end of the eighth resistor R8 is connected in series with a fourth light-emitting diode D4 and then coupled to the 5V DC voltage. The other end of the eighth resistor R8 is coupled to the main control chip U3. One end of the ninth resistor R9 is connected in series with a fifth light-emitting diode D5 and then coupled to the 5V DC voltage. The other end of the ninth resistor R9 is coupled to the main control chip U3.

[0078] The main control chip U3 includes twenty pins. The first pin of the main control chip U3 is the power supply terminal. A sixth capacitor C6 is connected in series to the first pin of the main control chip U3 and then coupled to a 5V DC voltage. The third pin of the main control chip U3 is coupled to the other end of an eighth resistor R8. The fourth pin of the main control chip U3 is coupled to a crystal oscillator Y1. The other end of the crystal oscillator Y1 is coupled to the fifth pin of the main control chip U3. A connection node where the crystal oscillator Y1 is coupled to the fourth pin of the main control chip U3 is coupled to a third capacitor C3, and the other end of the third capacitor C3 is grounded. A connection node where the crystal oscillator Y1 is coupled to the fifth pin of the main control chip U3 is coupled to a fourth capacitor C4, and the other end of the fourth capacitor C4 is grounded. The sixth pin of the main control chip U3 is the adjustment signal input terminal. The sixth pin of the main control chip U3 is coupled to a connection node between a switch S1 and a seventh TVS diode D7. The seventh pin of the main control chip U3 is coupled to the seventh pin of a conversion chip U2. The eighth and ninth pins of the main control chip U3 are analog signal output terminals. The eighth and ninth pins of the main control chip U3 are respectively coupled to an electrocardiogram analog signal module 3. The eighth pin of the main control chip U3 is also coupled to a second TVS diode D2, and the other end of the second TVS diode D2 is grounded. The ninth pin of the main control chip U3 is also coupled to a third TVS diode D3, and the other end of the third TVS diode D3 is grounded. The tenth pin of the main control chip U3 is grounded. The eleventh pin of the main control chip U3 is coupled to the other end of a ninth resistor R9. The twelfth to nineteenth pins of the main control chip U3 are control signal output terminals. The twelfth to nineteenth pins of the main control chip U3 are respectively coupled to a switch module 5. The twelfth pin of the main control chip U3 is also grounded through a sixteenth TVS diode D16 in series. The thirteenth pin of the main control chip U3 is also grounded through a fifteenth TVS diode D15 in series. The fourteenth pin of the main control chip U3 is also grounded through a fourteenth TVS diode D14 in series. The fifteenth pin of the main control chip U3 is also grounded through a thirteenth TVS diode D13 in series. The sixteenth pin of the main control chip U3 is also grounded through a twelfth TVS diode D12 in series. The seventeenth pin of the main control chip U3 is also grounded through an eleventh TVS diode D11 in series. The eighteenth pin of the main control chip U3 is also grounded through a tenth TVS diode D10 in series. The nineteenth pin of the main control chip U3 is also grounded through a ninth TVS diode D9 in series. The twentieth pin of the main control chip U3 is coupled to a 5V DC voltage through a sixth inductor L6 in series. The twentieth pin of the main control chip U3 is also coupled to an eighth TVS diode D8, and the other end of the eighth TVS diode D8 is grounded. A connection node where the twentieth pin of the main control chip U3 is coupled to the sixth inductor L6 is coupled to a tenth capacitor C10, and the other end of the tenth capacitor C10 is grounded. An eleventh capacitor C11 is connected in parallel across both ends of the tenth capacitor C10.

[0079] Specifically, the main control chip U3 inputs a 5V DC voltage through the first pin, and the main control chip U3 is powered on and starts. The main control chip U3 uses the crystal oscillator Y1 to provide an oscillation clock signal through the fourth and fifth pins to work, and forms an analog signal through the eighth and ninth pins and outputs it to the electrocardiogram analog signal module 3. The second TVS tube D2 and the third TVS tube D3 absorb the transient pulse impacts generated by external interference in the circuit of the main control module 2, improving the stability of the analog signal transmission. The state of the switch S1 is detected through the sixth pin of the main control chip U3, and an impedance adjustment signal is received. A control signal is provided according to the state of the switch S1, and the control signal is output to the switch module 5 through the twelfth to nineteenth pins; the main control chip U3 outputs a drive signal through the third and eleventh pins to light up the light-emitting diode D4 and the light-emitting diode D5, which are used to indicate the state of the switch S1; the eighth TVS tube D8 to the sixteenth TVS tube D16 absorb the transient pulse impacts generated by external interference in the circuit of the main control module 2, reducing the interference of electromagnetic signals on the circuit of the main control module 2.

[0080] Refer to Figure 7 , the electrocardiogram analog signal module 3 includes an analog chip U1. The analog chip U1 includes eight pins. The first pin of the analog chip U1 is an output terminal. The first pin of the analog chip U1 is connected in series with the eleventh resistor R11 and then coupled to the impedance module 6. The second pin of the analog chip U1 is grounded. The third and fourth pins of the analog chip U1 are analog signal input terminals. The third pin of the analog chip U1 is coupled to the eighth pin of the main control chip U3. The fourth pin of the analog chip U1 is coupled to the ninth pin of the main control chip U3. The fifth and sixth pins of the analog chip U1 are both grounded. The seventh pin of the analog chip U1 is a power supply terminal. The seventh pin of the analog chip U1 is coupled with a fifth capacitor C5. The other end of the fifth capacitor C5 is grounded. The two ends of the fifth capacitor C5 are connected in parallel with a second capacitor C2. The two ends of the second capacitor C2 are connected in parallel with a first TVS tube D1. The connection node of the first TVS tube D1 and the second capacitor C2 is coupled with a fifth inductor L5. The other end of the fifth inductor L5 is coupled to the 5V DC voltage. The eighth pin of the conversion chip U1 is coupled to the 5V DC voltage.

[0081] Specifically, the third and fourth pins of the analog chip U1 receive the analog signal output by the main control chip U3, and form an electrocardiogram analog signal and output it to the impedance module 6 through the first pin. The fifth inductor L5, the second capacitor C2, and the fifth capacitor C5 constitute an L-type filter circuit, which is used to eliminate the influence of electromagnetic interference on the internal circuit of the electrocardiogram analog signal module 3.

[0082] Refer to Figure 8, the switch module 5 includes four optocoupler chips U4 - U7, and the impedance module 6 includes resistors R22 to R29. Resistors R22, R24 to R29 form a parallel resistor network, and resistor R34 is connected in series with the parallel resistor network.

[0083] Each optocoupler chip includes eight pins. The first pin of optocoupler chip U4 is connected in series with resistor R13 and then coupled to a 5V DC voltage. The second pin of optocoupler chip U4 is coupled to the nineteenth pin of the main control chip U3. The third pin of optocoupler chip U4 is connected in series with resistor R14 and then coupled to a 5V DC voltage. The fourth pin of optocoupler chip U4 is coupled to the eighteenth pin of the main control chip U3. The fifth pin of optocoupler chip U4 is connected in series with resistor R11 and then coupled to the first pin of the analog chip U1. The fifth pin of optocoupler chip U4 is also coupled to resistor R32 and then coupled to the hemodynamic detection terminal 7. The fifth pin of optocoupler chip U4 is also coupled to the seventh pin of optocoupler chip U4. The sixth pin of optocoupler chip U4 is coupled to resistor R24 in the parallel resistor network. The seventh pin of optocoupler chip U4 is coupled to resistor R31, and the other end of resistor R31 is coupled to the hemodynamic detection terminal 7. The seventh pin of optocoupler chip U4 is also coupled to resistor R23. The eighth pin of optocoupler chip U4 is coupled to resistor R22, and the connection node of resistor R22 and resistor R23 is coupled to resistor R34, and the other end of resistor R34 is grounded.

[0084] The first pin of optocoupler chip U5 is connected in series with resistor R15 and then coupled to a 5V DC voltage. The second pin of optocoupler chip U5 is coupled to the sixteenth pin of the main control chip U3. The third pin of optocoupler chip U5 is connected in series with resistor R16 and then coupled to a 5V DC voltage. The fourth pin of optocoupler chip U5 is coupled to the seventeenth pin of the main control chip U3. The fifth pin of optocoupler chip U5 is coupled to the hemodynamic detection terminal 7. The fifth pin of optocoupler chip U5 is also coupled to the seventh pin of optocoupler chip U5. The sixth pin of optocoupler chip U5 is coupled to resistor R26 in the parallel resistor network. The seventh pin of optocoupler chip U5 is coupled to resistor R33, and the other end of resistor R33 is coupled to the hemodynamic detection terminal 7. The seventh pin of optocoupler chip U5 is also coupled to resistor R23. The eighth pin of optocoupler chip U5 is coupled to resistor R25 in the parallel resistor network.

[0085] The first pin of the optocoupler chip U6 is connected in series with the seventeenth resistor R17 and then coupled to the 5V DC voltage. The second pin of the optocoupler chip U6 is coupled to the fifteenth pin of the main control chip U3. The third pin of the optocoupler chip U6 is connected in series with the eighteenth resistor R18 and then coupled to the 5V DC voltage. The fourth pin of the optocoupler chip U6 is coupled to the fourteenth pin of the main control chip U3. The fifth pin of the optocoupler chip U6 is coupled to the seventh pin of the optocoupler chip U6. The sixth pin of the optocoupler chip U6 is coupled to the twenty-eighth resistor R28 in the parallel resistor network. The seventh pin of the optocoupler chip U6 is coupled to the twenty-third resistor R23. The eighth pin of the optocoupler chip U6 is coupled to the twenty-seventh resistor R27 in the parallel resistor network.

[0086] The first pin of the optocoupler chip U7 is connected in series with the nineteenth resistor R19 and then coupled to the 5V DC voltage. The second pin of the optocoupler chip U7 is coupled to the thirteenth pin of the main control chip U3. The third pin of the optocoupler chip U7 is connected in series with the twentieth resistor R20 and then coupled to the 5V DC voltage. The fourth pin of the optocoupler chip U7 is coupled to the twelfth pin of the main control chip U3. The fifth pin of the optocoupler chip U7 is coupled to the seventh pin of the optocoupler chip U7. The fifth pin of the optocoupler chip U7 is also coupled with the thirtieth resistor R30, and the other end of the thirtieth resistor R30 is coupled to the twenty-ninth resistor R29 in the parallel resistor network. The seventh pin of the optocoupler chip U7 is coupled to the twenty-third resistor R23. The eighth pin of the optocoupler chip U7 is coupled to the twenty-ninth resistor R29 in the parallel resistor network.

[0087] Specifically, when the optocoupler chip receives the change of the control signal output by the main control chip U3, the optocoupler chips U4 - U7 are in a conducting or non-conducting state according to the control signal, so that each resistor or part of the resistors in the parallel resistor network formed by the twenty-second resistor R22, the twenty-fourth resistor R24 to the twenty-ninth resistor R29, and the twenty-third resistor R23 form resistors with different resistance values, thereby simulating different impedances generated when human blood flows. Then, together with the thirty-fourth resistor R34 and the eleventh resistor R11, they form a series voltage-dividing resistor circuit to divide the electrocardiogram analog signal, and then output the electrocardiogram analog signal after voltage division to the blood flow dynamics detection terminal 7.

[0088] The implementation principle of an electrocardiogram (ECG) signal generation device simulating the human body in an embodiment of this application is as follows: The power conversion module 1 converts the power supply voltage into the operating voltages for the main control module 2, the ECG analog signal module 3, the adjustment module 4, and the switch module 5. The main control module 2 outputs an analog signal to the ECG analog signal module 3. After receiving the analog signal, the ECG analog signal module 3 forms an ECG analog signal. Medical staff generate an impedance adjustment signal through the adjustment module 4 and output it to the main control module 2. After receiving the impedance adjustment signal, the main control module 2 generates a control signal and outputs it to the switch module 5. The switch module 5 outputs a switch signal to the impedance module 6 according to the control signal to control the on / off status of each resistor sub-circuit in the impedance module 6. The impedance module 6 generates different resistance values based on the on / off status of its internal resistor sub-circuits, forms different impedance values based on different resistance values, and then simulates the different impedances generated when human blood flows. The ECG analog signal module 3 performs voltage division processing on the ECG analog signal through the impedance module 6 and outputs the processed ECG analog signal to the hemodynamic detection terminal 7 to complete the hemodynamic parameter simulation test process.

[0089] The above are all the preferred embodiments of this application. It does not limit the protection scope of this application accordingly. Therefore, all equivalent changes made according to the structure, shape, and principle of this application should be covered within the protection scope of this application.

Claims

1. A method for generating an analog human electrocardiogram signal, characterized in that: The described method for generating an analog human electrocardiogram (ECG) signal includes the steps of: The main control module generates ECG analog signal parameters, inputs the ECG analog signal parameters into the ECG analog signal module, and the ECG analog signal module outputs an ECG analog signal to the impedance network; Generate an impedance adjustment instruction according to the input result of the adjustment module, and adjust the impedance value output by the impedance terminal based on the impedance adjustment instruction; Input the impedance value into the ECG analog signal to obtain a blood flow simulated ECG signal; Output the blood flow simulated ECG signal to the blood flow dynamics detection terminal, and generate a blood flow parameter detection report based on the blood flow simulated ECG signal.

2. The method for generating an analog human electrocardiogram signal according to claim 1, characterized in that: The generating an impedance adjustment instruction according to the state of the adjustment module and adjusting the impedance value output by the impedance terminal based on the impedance adjustment instruction specifically includes: Input the impedance adjustment instruction into the impedance terminal, and the impedance terminal accesses different resistors according to the impedance adjustment instruction; Based on the parallel connection of different accessed resistors, different resistance values are generated, and the impedance terminal generates different impedance values based on the different resistance values.

3. A method for generating an analog human electrocardiogram signal according to claim 1, characterized in that: Before generating the ECG analog signal parameters, inputting the ECG analog signal parameters into the ECG analog signal module, and the ECG analog signal module outputting the ECG analog signal to the impedance network, it further includes: Obtain an analog bioelectrical muscle signal based on a blood flow dynamics parameter detection instruction, and perform rejection filtering processing on the analog bioelectrical muscle signal; Use the analog bioelectrical muscle signal after rejection filtering as the ECG analog signal.

4. An artificial body electrocardiogram signal generating device, based on the artificial body electrocardiogram signal generating method according to any one of claims 1-3, characterized in that: It includes a main control module (2), an ECG analog signal module (3), an adjustment module (4), a switch module (5), and an impedance module (6). The input end of the ECG analog signal module (3) is coupled to the main control module (2), the output end of the ECG analog signal module (3) is connected in series with the impedance module (6) and then coupled to the blood flow dynamics detection terminal (7). The adjustment module (4) is electrically connected to the main control module (2), and the adjustment module (4) is used to output an impedance adjustment signal to the main control module (2). The input end of the switch module (5) is coupled to the main control module (2), the output end of the switch module (5) is connected in series with the impedance module (6), the main control module (2) is used to output a control signal to the switch module (5) after receiving the impedance adjustment signal, the switch module (5) is used to control the on / off of the impedance module (6) according to the control signal, and the impedance module (6) outputs different impedance values according to the on / off situation.

5. A simulated human electrocardiogram signal generating device according to claim 4, characterized in that: It further includes a power conversion module (1). The input end of the power conversion module (1) is coupled to a power supply, and the output end of the power conversion module (1) is respectively coupled to the main control module (2), the ECG analog signal module (3), the adjustment module (4), and the switch module (5). The power conversion module (1) is used to provide a supply voltage for the analog human ECG signal generating device.

6. The analog human electrocardiogram signal generating device according to claim 4, wherein: The main control module (2) includes a main control chip U3. The main control chip U3 includes an adjustment signal input terminal, a control signal output terminal, and an analog signal output terminal. The adjustment signal input terminal of the main control chip U3 is coupled to the adjustment module (4) to input an impedance adjustment signal. The analog signal output terminal of the main control chip U3 is coupled to the electrocardiogram analog signal module (3) to output an analog signal to the electrocardiogram analog signal module (3). The control signal output terminal of the main control chip U3 is coupled to the switch module (5) to output a control signal to the switch module (5). The power supply terminal of the main control chip U3 is coupled to the power conversion module (1) to input an operating voltage.

7. An artificial body electrocardiogram signal generating apparatus according to claim 6, characterized in that: The electrocardiogram analog signal module (3) includes an analog chip U1. The analog chip U1 includes an analog signal input terminal and an output terminal. The analog signal input terminal of the analog chip U1 is coupled to the analog signal output terminal of the main control chip U3 to receive an analog signal. The output terminal of the analog chip U1 is coupled to the hemodynamic detection terminal (7) in series after being connected in series with the impedance module (6). The power supply terminal of the analog chip U1 is coupled to the power conversion module (1) after being connected in series with a filter circuit.

8. A device for generating an analog human electrocardiogram signal according to claim 7, characterized in that: The switch module (5) includes a plurality of optocoupler chips. The input terminal of each optocoupler chip is coupled to the control signal output terminal of the main control chip U3 to receive a control signal. The output terminal of each optocoupler chip is coupled to the impedance module (6) to output a switching signal to the impedance module (6).

9. The analog human electrocardiogram signal generating device according to claim 8, wherein: The impedance module (6) includes a parallel resistor network and two resistors. The parallel resistor network includes a plurality of resistors connected in parallel with each other. The parallel resistor network and the two resistors are connected in series with each other. One end of the parallel resistor network is respectively coupled to the output terminal of the optocoupler chip and the output terminal of the analog chip U1. The other end of the parallel resistor network is coupled to the hemodynamic detection terminal (7).

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