An anti-interference fast absorption transient pulse method and system

Abstract

This application relates to the technical field of weak signal processing, and in particular to an anti-interference fast absorption transient pulse method and system. The anti-interference fast absorption transient pulse method includes the steps of: generating an electrocardiogram analog signal based on the bioelectrical muscle signal, and setting and adjusting the analog impedance parameter based on the impedance value generated by the human body blood flow; constructing a signal processing model according to the analog impedance parameter, inputting the electrocardiogram analog signal into the signal processing model to obtain a human body blood flow analog signal; inputting the human body blood flow analog signal into a preset signal filtering model to obtain a standard electrocardiogram analog signal; calculating hemodynamic parameter data based on the standard electrocardiogram analog signal, and integrating the hemodynamic parameter data to form a hemodynamic parameter measurement report. This application has the effect of reducing the interference of electromagnetic signals on weak electrocardiogram signals and improving the anti-EMC interference effect.

Description

Technical Field

[0001] This application relates to the technical field of weak signal processing, and particularly to an anti-interference fast absorption transient pulse method and system. Background Art

[0002] With the improvement of people's living standards, there have been great changes in people's lifestyles and dietary structures, which has also led to an increasing prevalence of cardiovascular diseases. Cardiovascular diseases have become common and major diseases that endanger people's physical health, and how to prevent cardiovascular diseases has received more and more attention.

[0003] Collecting cardiovascular hemodynamic parameters plays an important role in the diagnosis of cardiovascular diseases. Existing measurement methods for hemodynamic parameters mainly include two types. One is the invasive measurement method, and the other is the non-invasive simulation measurement method. The invasive hemodynamic parameter measurement method has certain surgical risks and high medical costs. The non-invasive simulation hemodynamic parameter measurement method uses electrodes to collect the myoelectric signals generated by the human body and converts the myoelectric signals into electrocardiogram simulation signals. The non-invasive hemodynamic measurement device uses the electrocardiogram simulation signals to simulate and measure the human hemodynamic parameters to diagnose the health status of the human cardiovascular system.

[0004] However, the electrocardiogram simulation signal output to the non-invasive hemodynamic measurement device is a weak signal, which is extremely vulnerable to electromagnetic fields or human static electricity interference, easily distorts and makes the electrocardiogram simulation signal unstable, and further makes the measured hemodynamic parameters inaccurate, affecting the diagnosis result. Therefore, there is still room for improvement. Summary of the Invention

[0005] In order to reduce the interference of electromagnetic signals on weak electrocardiogram signals and improve the anti-EMC interference effect, this application provides an anti-interference fast absorption transient pulse method and system.

[0006] In a first aspect, this application provides an anti-interference fast absorption transient pulse method, adopting the following technical solution:

[0007] An anti-interference fast absorption transient pulse method, the anti-interference absorption fast transient pulse method includes the steps of:

[0008] Generating an electrocardiogram simulation signal based on a biological myoelectric signal model, and setting and adjusting simulation impedance parameters based on an impedance value model generated by human blood flow;

[0009] Constructing a signal processing model according to the simulation impedance parameters, and inputting the electrocardiogram simulation signal into the signal processing model to obtain a human blood flow simulation signal;

[0010] Inputting the human blood flow simulation signal into a preset signal filtering model to obtain a standard electrocardiogram simulation signal;

[0011] Calculate hemodynamic parameter data based on the standard electrocardiogram simulation signal, and integrate the hemodynamic parameter data to form a hemodynamic parameter measurement report.

[0012] By adopting the above technical solution, during the non-invasive hemodynamic measurement process, an electrocardiogram simulation signal is generated using the myoelectric signal of the human body as a model. At the same time, the simulated impedance parameter inside the non-invasive hemodynamic simulation device is adjusted according to the impedance value generated by the human blood flow. A signal processing model is constructed based on the simulated impedance parameter to perform signal processing on the electrocardiogram simulation signal to obtain a human blood flow simulation signal, simulating the real situation under the influence of the impedance change generated when the electrocardiogram signal flows in the human blood, making the electrocardiogram simulation signal more conform to the real human situation. The preset signal filtering model is used to filter the human blood flow simulation signal to obtain a standard electrocardiogram simulation signal to reduce the interference effect of external factors or human static electricity on the signal. By comparing and measuring the hemodynamic parameters through the standard electrocardiogram simulation signal, the accuracy of the hemodynamic parameter measurement results can be improved.

[0013] In a preferred example of the present application, it can be further configured that: setting and adjusting the simulated impedance parameter based on the impedance value model generated by the human blood flow specifically includes:

[0014] Obtain human blood flow impedance data, and establish a blood flow impedance value model based on the blood flow impedance data;

[0015] Generate an impedance adjustment instruction according to the human blood flow impedance value model, and set to conduct part or all of the resistor circuits based on the impedance adjustment instruction;

[0016] Based on the conduction situation of the resistor circuit, obtain multiple different resistance values, and combine the multiple different resistance values to obtain the simulated impedance parameter.

[0017] By adopting the above technical solution, the impedance value generated when the human body's blood flows is calculated by collecting the blood pressure value of the human body. An impedance adjustment instruction is generated based on the human blood flow impedance value to control part or all of the resistor circuits to conduct, obtaining different resistance value data, and combining according to different resistance values to obtain an impedance parameter that matches the impedance value when the human body's blood flows, realizing the function of simulating different impedance values generated by the human blood flow.

[0018] In a preferred example of the present application, it can be further configured that: inputting the electrocardiogram simulation signal into the signal processing model to obtain a human blood flow simulation signal specifically includes:

[0019] Obtain the characteristic data of the human blood flow simulation signal, and input the characteristic data into the signal filtering model to obtain electrocardiogram simulation characteristic data;

[0020] Form a standard electrocardiogram simulation signal based on the electrocardiogram simulation feature data.

[0021] By adopting the above technical solution, the human blood flow simulation signal is decomposed to obtain the feature data of the human blood flow simulation signal. The signal filtering model is used to screen the feature data, and the interference data in the feature data is filtered out, so as to obtain the electrocardiogram simulation feature data. Based on the electrocardiogram simulation feature data, a standard electrocardiogram simulation signal is formed, realizing the filtering function of the signal, and thus improving the accuracy of the output electrocardiogram simulation signal.

[0022] In a preferred example of the present application, it can be further configured that: before inputting the human blood flow simulation signal into a preset signal filtering model to obtain a standard electrocardiogram simulation signal, it further includes:

[0023] Detect whether the human blood flow simulation signal carries a transient pulse signal;

[0024] If so, perform absorption processing on the human blood flow simulation signal with a transient pulse signal.

[0025] By adopting the above technical solution, before filtering the human blood flow simulation signal, it is detected whether the human blood flow simulation signal is mixed with a transient pulse signal. If there is a transient pulse signal, absorption processing is performed on the human blood flow simulation signal to absorb and remove the transient pulse signal, thereby improving the anti-EMC interference performance of the signal.

[0026] In a second aspect, the present application provides an anti-interference fast absorption transient pulse system, adopting the following technical solution:

[0027] An anti-interference fast absorption transient pulse system is applied to a non-invasive hemodynamic simulation device, and includes an electrocardiogram simulation signal generation module, an impedance simulation module, an anti-interference module, and a measurement module. The output end of the electrocardiogram simulation signal generation module is coupled to the impedance simulation module. The electrocardiogram simulation signal generation module outputs an electrocardiogram simulation signal to the impedance simulation module based on the human myoelectric signal model. The output end of the impedance simulation module is coupled to the measurement module. The impedance simulation module is used to generate impedance parameters to simulate the impedance value generated by the signal when the human blood flows. The anti-interference module is electrically connected between the impedance simulation module and the measurement module. The anti-interference module is used to absorb transient pulse signals. The measurement module is used to output hemodynamic parameter measurement data according to the electrocardiogram simulation signal.

[0028] By adopting the above technical solution, an electrocardiogram (ECG) simulation signal generation module is arranged in the non-invasive hemodynamic simulation device. An ECG simulation signal of the human body is formed by using the human electromyogram signal model. An impedance parameter is generated by the impedance simulation module to simulate the human impedance value generated during human blood flow, thereby more accurately simulating the human blood flow process. The impedance parameter of the impedance simulation module performs voltage division processing on the ECG simulation signal. The ECG simulation signal after voltage division processing is input into the measurement module. An anti-interference module is arranged in front of the measurement module, and the anti-interference module is used to remove interference from the ECG simulation signal input into the measurement module. The anti-interference module absorbs transient pulse signals generated by the internal circuit of the system and / or external static electricity, thereby effectively reducing the interference of electromagnetic signals on weak ECG signals and improving the anti-EMC interference effect of the non-invasive hemodynamic simulation device.

[0029] Preferably, the ECG simulation signal generation module includes a DAC analog sub-module and a main control sub-module. The main control sub-module includes an ECG signal parameter terminal and an impedance control terminal. The output terminal of the ECG signal parameter terminal of the main control sub-module outputs an ECG signal parameter according to the electromyogram signal model generated by the human body. The impedance control terminal of the main control sub-module is coupled to the impedance simulation module. The input terminal of the DAC analog sub-module is coupled to the main control sub-module, and the output terminal of the DAC analog sub-module is coupled to the impedance simulation module to output an ECG simulation signal to the impedance module.

[0030] By adopting the above technical solution, the main control sub-module outputs an analog ECG signal parameter to the DAC analog sub-module through the human electromyogram signal model. The DAC analog sub-module converts the electromyogram signal into an ECG simulation signal and outputs it to the impedance simulation module. At the same time, the impedance control sub-module outputs an adjustment signal to the impedance simulation module through the impedance control terminal, so that the impedance simulation module adjusts the impedance parameter according to the adjustment signal to perform voltage division processing on the ECG simulation signal, realizing the function of generating an ECG simulation signal.

[0031] Preferably, the impedance simulation module includes a switch sub-module and a series resistor network sub-module. The input terminal of the switch sub-module is coupled to the impedance control terminal of the main control sub-module. The output terminal of the switch sub-module is coupled to the series resistor network sub-module. The switch sub-module is used to adjust the resistance value generated by the series resistor network sub-module. The output terminal of the series resistor network sub-module is coupled to the measurement module in series after being connected to the anti-interference module. The connection node between the series resistor network sub-module and the switch sub-module is coupled to the DAC analog sub-module.

[0032] By adopting the above technical solution, after the switch sub-module receives the adjustment signal output by the main control sub-module, the switch module controls the resistance value of the series resistor network sub-module to change, generating different impedance parameters based on different resistance values, and realizing the simulation of different human impedance values generated during human blood flow.

[0033] Preferably, the anti-interference module includes a plurality of filter sub-modules and a plurality of TVS tubes. One end of the filter sub-module is connected in series with the output end of the series resistance network sub-module, and the other end of the filter sub-module serves as a lead wire interface and is electrically connected to the measurement module. The plurality of TVS tubes are respectively coupled in the filter sub-module.

[0034] By adopting the above technical solution, by setting the TVS tubes and utilizing the properties of the TVS tubes, the transient pulse impacts generated by the non-invasive hemodynamic simulation device due to external interference are absorbed, and the anti-EMC interference performance of the non-invasive hemodynamic simulation device is improved. Before the electrocardiogram analog signal is output to the measurement module, it undergoes filtering processing by the filter sub-module to eliminate the interference of the lead wire on the electrocardiogram analog signal, improve the stability of the electrocardiogram analog signal, and thus effectively improve the accuracy of the hemodynamic parameter measurement results.

[0035] Preferably, the filter sub-module includes two capacitors and an inductor. The two capacitors and the inductor are connected in series with each other. The connection node of one capacitor and the inductor is coupled to the series resistance network sub-module, and the connection node of the other capacitor and the inductor serves as a lead wire interface and is electrically connected to the measurement module. The connection node of the two capacitors is grounded.

[0036] By adopting the above technical solution, the connection method between the two capacitors and the inductor forms a Π-type filter circuit to remove the interference signals in the electrocardiogram analog signal input to the measurement module, making the electrocardiogram analog signal more stable and smooth, and thus effectively improving the accuracy of the hemodynamic parameter measurement.

[0037] In summary, the present application includes at least one of the following beneficial technical effects:

[0038] 1. The anti-interference module is used to remove interference from the electrocardiogram analog signal input to the measurement module. The anti-interference module absorbs the transient pulse signals generated by the internal circuit of the system and / or external static electricity, and thus can effectively reduce the interference of electromagnetic signals on the weak electrocardiogram signal, improving the anti-EMC interference effect of the non-invasive hemodynamic simulation device;

[0039] 2. By collecting the blood flow impedance value of the human body, the human blood flow impedance model is calculated. An impedance adjustment instruction is generated based on the human blood flow impedance model to control part or all of the resistance circuits to conduct, obtaining different resistance values. According to different combinations of the resistance values, impedance parameters matching the impedance value during human blood flow are obtained, realizing the function of simulating different impedance values generated by human blood flow;

[0040] 3. By setting up TVS tubes and utilizing the properties of TVS tubes, transient pulse impacts generated by external interference on the non-invasive hemodynamic simulation device are absorbed, improving the anti-EMC interference performance of the non-invasive hemodynamic simulation device. Before the electrocardiogram (ECG) simulation signal is output to the measurement module, it undergoes filtering processing by a filtering sub-module to eliminate the interference effect of the lead wire on the ECG simulation signal, improving the stability of the ECG simulation signal, and thus effectively enhancing the accuracy of the hemodynamic parameter measurement results. Brief Description of the Drawings

[0041] Figure 1 is a flowchart of an embodiment of a method for an anti-interference fast absorption transient pulse system of the present application.

[0042] Figure 2 is a flowchart for implementing step S10 in an embodiment of a method for an anti-interference fast absorption transient pulse system of the present application.

[0043] Figure 3 is a flowchart for implementing step S30 in an embodiment of a method for an anti-interference fast absorption transient pulse system of the present application.

[0044] Figure 4 is another flowchart of an embodiment of a method for an anti-interference fast absorption transient pulse system of the present application.

[0045] Figure 5 is a module structure diagram of an embodiment of an anti-interference fast absorption transient pulse system of the present application.

[0046] Figure 6 is a circuit diagram of an electrocardiogram (ECG) simulation signal generation module in an embodiment of an anti-interference fast absorption transient pulse system of the present application.

[0047] Figure 7 is a circuit diagram of an impedance simulation module and an anti-interference module in an embodiment of an anti-interference fast absorption transient pulse system of the present application.

[0048] Description of Reference Numerals: 1. Electrocardiogram (ECG) simulation signal generation module; 11. DAC analog sub-module; 12. Main control sub-module; 2. Impedance simulation module; 21. Switch sub-module; 22. Series resistor network sub-module; 3. Anti-interference module; 31. Filtering sub-module; 4. Measurement module. Detailed Embodiments

[0049] In order to make the objectives, technical solutions, and advantages of the present application clearer and more understandable, the following further elaborates on the present application in conjunction with the appended Figure 1-7 drawings.

[0050] In one embodiment, as Figure 1 shown, the present application discloses an anti-interference fast absorption transient pulse method, which specifically includes the following steps:

[0051] S10: Generate an electrocardiogram (ECG) simulation signal based on a biological electromyogram (EMG) signal model, and set and adjust simulation impedance parameters based on an impedance value model generated by human blood flow.

[0052] In this embodiment, the ECG simulation signal is a simulation signal of the EMG signal emitted by the human cardiovascular system, and the simulation impedance parameter refers to the simulated value of the impedance value generated by human blood flow.

[0053] Specifically, during the non-invasive hemodynamic measurement process, an ECG signal data model is established based on the collected EMG signal emitted by the human cardiovascular system, and simulation ECG signal parameters are formed according to the ECG signal data model.

[0054] Furthermore, by collecting the impedance value generated during human blood flow and adjusting the impedance parameters in the non-invasive hemodynamic simulation device, the impedance value in the non-invasive hemodynamic simulation device is made to match the value generated by human blood flow, thereby achieving the function of accurately simulating the actual human situation.

[0055] S20: Construct a signal processing model according to the simulation impedance parameter, and input the ECG simulation signal into the signal processing model to obtain a human blood flow simulation signal.

[0056] In this embodiment, the signal processing model refers to a model that analyzes the influence of impedance values on the ECG simulation signal, and the human blood flow simulation signal refers to a simulation signal that simulates the EMG signal generated by the cardiovascular system of the human body under normal blood flow conditions.

[0057] Specifically, based on the currently set impedance value in the non-invasive hemodynamic simulation device, a model that analyzes the influence of impedance values on the ECG simulation signal is constructed. The impedance value in this model is used to perform voltage division processing on the ECG simulation signal, obtaining a simulation signal that simulates the EMG signal generated by the cardiovascular system of the human body under normal blood flow conditions, making the ECG simulation signal more conform to the human simulation situation.

[0058] S30: Input the human blood flow simulation signal into a preset signal filtering model to obtain a standard ECG simulation signal.

[0059] In this embodiment, the signal filtering model refers to a model that filters and stabilizes the signal, and the standard ECG simulation signal refers to the ECG simulation signal after filtering processing.

[0060] Specifically, a signal filtering model is preset in the hemodynamic simulation device. The analog signal simulating the electromyogram signal generated by the cardiovascular system of the human body under normal blood flow conditions is input into the signal filtering model. The analog signal simulating the electromyogram signal generated by the cardiovascular system of the human body under normal blood flow conditions may have interference waves that are not conducive to testing due to the influence of the external environment or testing equipment. The signal filtering model is used to filter the analog signal simulating the electromyogram signal generated by the cardiovascular system of the human body under normal blood flow conditions, so as to reduce the interference influence of external factors or testing equipment on the signal.

[0061] S40: Calculate hemodynamic parameter data based on the standard electrocardiogram analog signal, and integrate the hemodynamic parameter data to form a hemodynamic parameter measurement report.

[0062] In this embodiment, the hemodynamic parameter data refers to the cardiovascular blood flow value, and the hemodynamic parameter measurement report refers to the cardiovascular numerical health report.

[0063] Specifically, perform hemodynamic parameter analysis and calculation on the filtered electrocardiogram analog signal to obtain the specific value of cardiovascular blood flow. Organize the specific value of cardiovascular blood flow into a cardiovascular numerical health report. Medical staff conduct comparative analysis on the human cardiovascular system based on the hemodynamic parameter detection report to achieve the ability to pre-detect the health status of the human cardiovascular system.

[0064] In this embodiment, during the non-invasive hemodynamic measurement process, an electrocardiogram analog signal model is established using the electromyogram signal of the human body. At the same time, the analog impedance parameters in the non-invasive hemodynamic simulation device are adjusted according to the impedance value generated by the human blood flow. A signal processing model is constructed based on the analog impedance parameters to perform signal processing on the electrocardiogram analog signal to obtain the human blood flow simulation signal, simulating the changes that occur under the influence of the impedance value generated when the signal is in the human blood flow, making the electrocardiogram analog signal more conform to the human simulation situation. The preset signal filtering model is used to filter the human blood flow simulation signal to obtain the standard electrocardiogram analog signal, so as to reduce the interference influence of external factors or human static electricity on the signal. By measuring hemodynamic parameters through the standard electrocardiogram analog signal, the accuracy of the hemodynamic parameter measurement results can be improved.

[0065] In one embodiment, as Figure 2 shown, in step S10, that is, adjusting the analog impedance parameters based on the impedance value model generated by the human blood flow, specifically includes:

[0066] S11: Obtain human blood flow impedance data, and calculate and establish a human blood flow impedance model based on the blood flow impedance data.

[0067] Specifically, a device for measuring human impedance, such as a monitor with hemodynamic measurement function, can be used to detect the human body, obtain data on impedance changes during human blood flow, and statistically calculate a model of impedance value changes generated during human cardiovascular blood flow from these data.

[0068] S12: Generate an impedance adjustment instruction according to the human blood flow impedance value change model, and set to conduct part or all of the resistance circuit based on the impedance adjustment instruction.

[0069] Specifically, taking the impedance value generated during human cardiovascular blood flow in step S11 as the reference value, medical staff trigger and generate a control instruction for adjusting and setting the impedance parameters of the hemodynamic simulation device, and control the conduction or disconnection of the resistance circuit in the hemodynamic simulation device.

[0070] S13: Based on the conduction situation of the resistance circuit, obtain multiple different resistance values, and combine the multiple different resistance values to obtain simulated impedance parameters.

[0071] Specifically, different numbers of conduction of the resistance circuit in the hemodynamic simulation device will generate multiple different resistance values. Different resistance values are combined to obtain a simulated value of the impedance value generated by human blood flow, realizing the function of simulating different impedance values generated by human blood flow.

[0072] In one embodiment, as Figure 3 shown, in step S30, inputting the human blood flow simulation signal into a preset signal filtering model to obtain a standard electrocardiogram simulation signal, specifically including:

[0073] S31: Obtain the characteristic data of the human blood flow simulation signal, and input the characteristic data into the signal filtering model to obtain electrocardiogram simulation characteristic data.

[0074] In this embodiment, the characteristic data refers to the signal characteristics of the human blood flow simulation signal, and the electrocardiogram simulation characteristic data refers to the signal characteristics simulating the beating of the human heart.

[0075] Specifically, decompose the human blood flow simulation signal to obtain the signal characteristics of the human blood flow simulation signal, which is convenient for screening and filtering the human blood flow simulation signal. Use the signal filtering model to screen the signal characteristics, and filter out the interference data in the characteristic data, where the interference data refers to static data and EMC data, etc., to obtain the signal characteristics simulating human blood flow, realizing the process of filtering the simulation signal.

[0076] S32: Form a standard electrocardiogram simulation signal based on the electrocardiogram simulation characteristic data.

[0077] Specifically, the human blood flow simulation signal is filtered to remove the interference signal in the human blood flow simulation signal, making the human blood flow simulation signal more stable. The signal characteristics of the simulated human cardiovascular system after filtering are used as the standard electrocardiogram simulation signal, and the standard electrocardiogram simulation signal is used for testing to achieve the function of improving the accuracy of blood flow dynamic parameter measurement.

[0078] In one embodiment, as Figure 3 shown, before step S30, that is, before the human blood flow simulation signal is input into a preset signal filtering model to obtain a standard electrocardiogram simulation signal, an anti-interference fast absorption transient pulse method further includes the steps:

[0079] S301: Detect whether the human blood flow simulation signal carries a transient pulse signal.

[0080] Specifically, the non-invasive blood flow dynamics simulation device will be interfered by external factors, such as the wires on the electrodes and the interference brought by the external environment, which will generate transient pulses during the measurement process. As a result, the human blood flow simulation signal will be mixed with transient pulse signals, which will affect the accuracy of the measurement results.

[0081] S302: If so, perform absorption processing on the human blood flow simulation signal with transient pulse signals.

[0082] Specifically, when it is detected that the human blood flow simulation signal contains transient pulse signals, the absorption circuit in the non-invasive blood flow dynamics simulation device is used for absorption processing to quickly absorb and remove the transient pulses, thereby improving the anti-EMC interference performance of the signal.

[0083] In one embodiment, the present application also discloses an anti-interference fast absorption transient pulse system, which corresponds one-to-one with the anti-interference absorption fast transient pulse method in the above embodiment. As Figure 5 shown, an anti-interference absorption fast transient pulse system applied to a non-invasive blood flow dynamics simulation device includes an electrocardiogram simulation signal generation module 1, an impedance simulation module 2, an anti-interference module 3, and a measurement module 4.

[0084] The electrocardiogram simulation signal generation module 1 generates a simulated electrocardiogram signal based on the human myoelectric signal model. The output end of the electrocardiogram simulation signal generation module 1 is coupled to the impedance simulation module 2. The output end of the impedance simulation module 2 is coupled to the measurement module 4. The anti-interference module 3 is electrically connected between the impedance simulation module 2 and the measurement module 4.

[0085] Specifically, the main control module generates an analog electrocardiogram signal based on the human electromyogram signal model and transmits it to the electrocardiogram analog signal generation module 1. The electrocardiogram analog signal generation module 1 uses the electromyogram signal model to form the electrocardiogram analog signal of the human body. The impedance simulation module 2 generates impedance parameters to simulate the impedance value generated by the human blood flow on the signal, accurately simulating the human blood flow process. The impedance parameters perform voltage division processing on the electrocardiogram analog signal. The electrocardiogram analog signal after voltage division processing is input to the measurement module 4. The anti-interference module 3 performs interference removal processing on the electrocardiogram analog signal input to the measurement module 4. The anti-interference module 3 absorbs the transient pulse signals generated by the internal circuit of the system and / or external static electricity.

[0086] Refer to Figure 5 and Figure 6 , the electrocardiogram analog signal generation module 1 includes a DAC analog sub-module 11 and a main control sub-module 12. The main control sub-module 12 includes a control chip U1. The control chip U1 includes twenty pins. The first pin of the control chip U1 is the power supply terminal, and the first pin of the control chip U1 is coupled to a 5V DC voltage. The fourth pin of the control chip U1 is coupled with a crystal oscillator Y1, and the other end of the crystal oscillator Y1 is coupled to the fifth pin of the control chip U1. The eighth and ninth pins of the control chip U1 are analog signal output terminals. The eighth and ninth pins of the control chip U1 are respectively coupled to the DAC analog sub-module 11. The eighth pin of the control chip U1 is also coupled with a second TVS tube D2, and the other end of the second TVS tube D2 is grounded. The ninth pin of the control chip U1 is also coupled with a third TVS tube D3, and the other end of the third TVS tube D3 is grounded. The twelfth to nineteenth pins of the control chip U1 are impedance control terminals, and the twelfth to nineteenth pins of the control chip U1 are respectively coupled to the impedance simulation module 2. The twelfth pin of the control chip U1 is also grounded through a sixteenth TVS tube D16 in series. The thirteenth pin of the control chip U1 is also grounded through a fifteenth TVS tube D15 in series. The fourteenth pin of the control chip U1 is also grounded through a fourteenth TVS tube D14 in series. The fifteenth pin of the control chip U1 is also grounded through a thirteenth TVS tube D13 in series. The sixteenth pin of the control chip U1 is also grounded through a twelfth TVS tube D12 in series. The seventeenth pin of the control chip U1 is also grounded through an eleventh TVS tube D11 in series. The eighteenth pin of the control chip U1 is also grounded through a tenth TVS tube D10 in series. The nineteenth pin of the control chip U1 is also grounded through a ninth TVS tube D9 in series. The twentieth pin of the control chip U1 is coupled to a 5V DC voltage through a sixth inductor L6 in series. The twentieth pin of the control chip U1 is also coupled with an eighth TVS tube D8, and the other end of the eighth TVS tube D8 is grounded. The connection node between the twentieth pin of the control chip U1 and the sixth inductor L6 is also coupled with 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.

[0087] The DAC analog sub-module 11 includes a signal conversion chip U2. The conversion chip U2 has eight pins. The first pin of the conversion chip U2 is the output terminal. The first pin of the conversion chip U2 is respectively connected in series with a tenth resistor R10 and an eleventh resistor R11 and then coupled to the impedance simulation module 2. The third pin of the conversion chip U2 is coupled to the eighth pin of the control chip U1. The fourth pin of the conversion chip U2 is coupled to the ninth pin of the control chip U1. The seventh pin of the conversion chip U2 is the power supply terminal, coupled to a 5V DC voltage, and the eighth pin of the conversion chip U1 is coupled to the 5V DC voltage.

[0088] Refer to Figure 5 and Figure 7 , the impedance simulation module 2 includes a switch sub-module 21 and a series resistor network sub-module 22. The series resistor network sub-module 22 includes a twenty-third resistor R23 and a parallel resistor network. The parallel resistor network is specifically composed of a twenty-second resistor R22, a twenty-fourth resistor R24 to a twenty-ninth resistor R29 connected in parallel with each other.

[0089] The switch sub-module 21 includes four switching tubes, namely switching tube U3, switching tube U4, switching tube U5, and switching tube U6. The structure of each switching tube is the same. The second pin of the switching tube U3 is coupled to the nineteenth pin of the control chip U1. The fourth pin of the switching tube U3 is coupled to the eighteenth pin of the control chip U1. The fifth pin of the switching tube U3 is coupled to the first pin of the conversion chip U2. The fifth pin of the switching tube U3 is connected in series with a thirty-second resistor R32 and then coupled to the anti-interference module 3. The fifth pin of the switching tube U3 is also coupled to the seventh pin of the switching tube U3. The sixth pin of the switching tube U3 is coupled to the twenty-fourth resistor R24 in the parallel resistor network. The seventh pin of the switching tube U3 is connected in series with a thirty-first resistor R31 and then coupled to the anti-interference module 3. The seventh pin of the switching tube U3 is also coupled to the twenty-third resistor R23. The eighth pin of the switching tube U3 is coupled to the twenty-second resistor R22. The connection node of the twenty-second resistor R22 and the twenty-third resistor R23 is coupled with a thirty-fourth resistor R34, and the other end of the thirty-fourth resistor R34 is grounded.

[0090] The second pin of the switching transistor U4 is coupled to the sixteenth pin of the control chip U1, the fourth pin of the switching transistor U4 is coupled to the seventeenth pin of the control chip U1, the fifth pin of the switching transistor U4 is coupled to the anti-interference module 3, the fifth pin of the switching transistor U4 is also coupled to the seventh pin of the switching transistor U4, the sixth pin of the switching transistor U4 is coupled to the twenty-sixth resistor R26 in the parallel resistor network, the seventh pin of the switching transistor U4 is coupled with a thirty-third resistor R33, the other end of the thirty-third resistor R33 is coupled to the anti-interference module 3, the seventh pin of the switching transistor U4 is also coupled to the twenty-third resistor R23, and the eighth pin of the switching transistor U4 is coupled to the twenty-fifth resistor R25 in the parallel resistor network.

[0091] The second pin of the switching transistor U5 is coupled to the fifteenth pin of the control chip U1, the fourth pin of the switching transistor U5 is coupled to the fourteenth pin of the control chip U1, the fifth pin of the switching transistor U5 is coupled to the anti-interference module 3 after being serially connected with a thirty-sixth resistor R36, the fifth pin of the switching transistor U5 is also coupled to the seventh pin of the switching transistor U5, the sixth pin of the switching transistor U5 is coupled to the twenty-eighth resistor R28 in the parallel resistor network, the seventh pin of the switching transistor U5 is coupled to the anti-interference module 3 after being serially connected with a thirty-fifth resistor R35, the seventh pin of the switching transistor U5 is also coupled to the twenty-third resistor R23, and the eighth pin of the switching transistor U5 is coupled to the twenty-seventh resistor R27 in the parallel resistor network.

[0092] The second pin of the switching transistor U6 is coupled to the thirteenth pin of the control chip U1, the fourth pin of the switching transistor U6 is coupled to the twelfth pin of the control chip U1, the fifth pin of the switching transistor U6 is coupled to the anti-interference module 3 after being serially connected with a thirtieth resistor R30 and a thirty-eighth resistor R38 in sequence, the fifth pin of the switching transistor U6 is also coupled to the seventh pin of the switching transistor U6, the connection node of the thirtieth resistor R30 and the thirty-eighth resistor R38 is coupled to the twenty-ninth resistor R29 in the parallel resistor network, the seventh pin of the switching transistor U6 is coupled to the anti-interference module 3 after being serially connected with a thirty-seventh resistor R37, the seventh pin of the switching transistor U6 is also coupled to the twenty-third resistor R23, and the eighth pin of the switching transistor U6 is coupled to the twenty-ninth resistor R29 in the parallel resistor network.

[0093] Refer to Figure 5 and Figure 7, the anti-interference module 3 includes a plurality of filtering sub-modules 31 and a plurality of TVS tubes. The plurality of TVS tubes specifically include sixteen TVS tubes, and the filtering sub-module 31 is specifically a Π-type filtering circuit composed of two capacitors and an inductor. The connection node of the tenth inductor L10 and the twelfth capacitor C12 is coupled to one end of the thirty-first resistor R31. One end of the eighteenth TVS tube D18 is coupled to the connection node of the tenth inductor L10 and the twelfth capacitor C12, and the other end of the eighteenth TVS tube D18 is grounded. The connection node of the tenth inductor L10 and the sixteenth capacitor C16 serves as a lead wire interface R1 for coupling with the measurement module 4. One end of the twenty-sixth TVS tube D26 is coupled to the connection node of the tenth inductor L10 and the sixteenth capacitor C16, and the other end of the twenty-sixth TVS tube D26 is grounded. The connection node of the twelfth capacitor C12 and the sixteenth capacitor C16 is grounded. One tenth inductor L10 and two capacitors C12 and C16 form a filtering sub-module 31.

[0094] The connection node of the seventh inductor L7 and the thirteenth capacitor C13 is coupled to one end of the thirty-second resistor R32. One end of the nineteenth TVS tube D19 is coupled to the connection node of the seventh inductor L7 and the thirteenth capacitor C13, and the other end of the nineteenth TVS tube D19 is grounded. The connection node of the seventh inductor L7 and the seventeenth capacitor C17 serves as a lead wire interface R2 for coupling with the measurement module 4. One end of the twenty-seventh TVS tube D27 is coupled to the connection node of the seventh inductor L7 and the seventeenth capacitor C17, and the other end of the twenty-seventh TVS tube D27 is grounded. The connection node of the thirteenth capacitor C13 and the seventeenth capacitor C17 is grounded.

[0095] The connection node of the eighth inductor L8 and the fourteenth capacitor C14 is coupled to one end of the thirty-third resistor R33. One end of the twentieth TVS tube D20 is coupled to the connection node of the eighth inductor L8 and the fourteenth capacitor C14, and the other end of the twentieth TVS tube D20 is grounded. The connection node of the eighth inductor L8 and the eighteenth capacitor C18 serves as a lead wire interface L1 for coupling with the measurement module 4. One end of the twenty-eighth TVS tube D28 is coupled to the connection node of the eighth inductor L8 and the eighteenth capacitor C18, and the other end of the twenty-eighth TVS tube D28 is grounded. The connection node of the fourteenth capacitor C14 and the eighteenth capacitor C18 is grounded.

[0096] The connection node of the ninth inductor L9 and the fifteenth capacitor C15 is coupled to the fifth pin of the switching transistor U4. One end of the twenty-first TVS diode D21 is coupled to the connection node of the ninth inductor L9 and the fifteenth capacitor C15, and the other end of the twenty-first TVS diode D21 is grounded. The connection node of the ninth inductor L9 and the nineteenth capacitor C19 serves as a lead wire interface L2 for coupling with the measurement module 4. One end of the twenty-ninth TVS diode D29 is coupled to the connection node of the ninth inductor L9 and the nineteenth capacitor C19, and the other end of the twenty-ninth TVS diode D29 is grounded. The connection node of the fifteenth capacitor C15 and the nineteenth capacitor C19 is grounded.

[0097] The connection node of the eleventh inductor L11 and the twentieth capacitor C20 is coupled to the other end of the thirty-fifth resistor R35. One end of the twenty-second TVS diode D22 is coupled to the connection node of the eleventh inductor L11 and the twentieth capacitor C20, and the other end of the twenty-second TVS diode D22 is grounded. The connection node of the eleventh inductor L11 and the twenty-fourth capacitor C24 serves as a lead wire interface L3 for coupling with the measurement module 4. One end of the thirtieth TVS diode D30 is coupled to the connection node of the eleventh inductor L11 and the twenty-fourth capacitor C24, and the other end of the thirtieth TVS diode D30 is grounded. The connection node of the twentieth capacitor C20 and the twenty-fourth capacitor C24 is grounded.

[0098] The connection node of the twelfth inductor L12 and the twenty-first capacitor C21 is coupled to the other end of the thirty-sixth resistor R36. One end of the twenty-third TVS diode D23 is coupled to the connection node of the twelfth inductor L12 and the twenty-first capacitor C21, and the other end of the twenty-third TVS diode D23 is grounded. The connection node of the twelfth inductor L12 and the twenty-fifth capacitor C25 serves as a lead wire interface R3 for coupling with the measurement module 4. One end of the thirty-first TVS diode D31 is coupled to the connection node of the twelfth inductor L12 and the twenty-fifth capacitor C25, and the other end of the thirty-first TVS diode D31 is grounded. The connection node of the twenty-first capacitor C21 and the twenty-fifth capacitor C25 is grounded.

[0099] The connection node of the thirteenth inductor L13 and the twenty-second capacitor C22 is coupled to the other end of the thirty-seventh resistor R37. One end of the twenty-fourth TVS diode D24 is coupled to the connection node of the thirteenth inductor L13 and the twenty-second capacitor C22, and the other end of the twenty-fourth TVS diode D24 is grounded. The connection node of the thirteenth inductor L13 and the twenty-sixth capacitor C26 serves as a lead wire interface L4 for coupling with the measurement module 4. One end of the thirty-second TVS diode D32 is coupled to the connection node of the thirteenth inductor L13 and the twenty-sixth capacitor C26, and the other end of the thirty-second TVS diode D32 is grounded. The connection node of the twenty-second capacitor C22 and the twenty-sixth capacitor C26 is grounded.

[0100] The connection node of the fourteenth inductor L14 and the twenty-third capacitor C23 is coupled to the other end of the thirty-eighth resistor R38. One end of the twenty-fifth TVS diode D25 is coupled to the connection node of the fourteenth inductor L14 and the twenty-third capacitor C23. The other end of the twenty-fifth TVS diode D25 is grounded. The connection node of the fourteenth inductor L14 and the twenty-seventh capacitor C27 serves as a lead wire interface R4 for coupling to the measurement module 4. One end of the thirty-third TVS diode D33 is coupled to the connection node of the fourteenth inductor L14 and the twenty-seventh capacitor C27. The other end of the thirty-third TVS diode D33 is grounded. The connection node of the twenty-third capacitor C23 and the twenty-seventh capacitor C27 is grounded.

[0101] The implementation principle of an anti-interference and fast transient pulse absorption system in an embodiment of this application is as follows: The electrocardiogram (ECG) simulation signal generation module 1 in the non-invasive hemodynamic simulation device forms an ECG simulation signal of the human body based on the myoelectric signal model generated by the human body. The impedance simulation module 2 generates impedance parameters. The impedance simulation module 2 generates impedance parameters to accurately simulate the human blood flow process. The impedance parameters perform voltage division processing on the ECG simulation signal. The ECG simulation signal after voltage division processing is input into the measurement module 4. The filtering sub-module 31 in the anti-interference module 3 performs filtering processing to eliminate the interference effect of the lead wire on the ECG simulation signal. The TVS diodes in the anti-interference module 3 absorb the transient pulse impact generated by the non-invasive hemodynamic simulation device being interfered by the outside world, improve the anti-EMC interference performance of the non-invasive hemodynamic simulation device, improve the stability of the ECG simulation signal, and thus effectively improve the accuracy of the hemodynamic parameter measurement result.

[0102] The above are all 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 measuring hemodynamic parameters, characterized in that: Including the steps: Generating an electrocardiogram (ECG) simulation signal based on a biological electromyogram signal model, and setting and adjusting simulation impedance parameters based on an impedance value model generated by human blood flow; Constructing a signal processing model according to the simulation impedance parameters, and inputting the ECG simulation signal into the signal processing model to obtain a human blood flow simulation signal; Inputting the human blood flow simulation signal into a preset signal filtering model to obtain a standard ECG simulation signal; Calculating hemodynamic parameter data based on the standard ECG simulation signal, and integrating the hemodynamic parameter data to form a hemodynamic parameter measurement report.

2. The hemodynamic parameter measurement method according to claim 1, wherein: Setting and adjusting simulation impedance parameters based on an impedance value model generated by human blood flow, specifically including: Obtaining human blood flow impedance data, and establishing a blood flow impedance value model based on the blood flow impedance data; Generating an impedance adjustment instruction according to the blood flow impedance value model, and setting to turn on part or all of the resistor circuits based on the impedance adjustment instruction; Based on the conduction condition of the resistor circuits, obtaining a plurality of different resistance values, and combining the plurality of different resistance values to obtain simulation impedance parameters.

3. A method for measuring hemodynamic parameters according to claim 1, characterized in that: Inputting the human blood flow simulation signal into a preset signal filtering model to obtain a standard ECG simulation signal, specifically including: Obtaining characteristic data of the human blood flow simulation signal, and inputting the characteristic data into the signal filtering model to obtain ECG simulation characteristic data; Forming a standard ECG simulation signal based on the ECG simulation characteristic data.

4. A hemodynamic parameter measurement method according to claim 3, characterized in that: Before inputting the human blood flow simulation signal into a preset signal filtering model to obtain a standard ECG simulation signal, it further includes: Detecting whether the human blood flow simulation signal carries a transient pulse signal; If so, performing absorption processing on the human blood flow simulation signal carrying the transient pulse signal.

5. An anti-interference fast absorption transient pulse system, based on the blood flow dynamic parameter measurement method according to any one of claims 1-3, characterized in that: Including an ECG simulation signal generation module (1), an impedance simulation module (2), an anti-interference module (3), and a measurement module (4). The output end of the ECG simulation signal generation module (1) is coupled to the impedance simulation module (2). The ECG simulation signal generation module (1) outputs an ECG simulation signal to the impedance simulation module (2) based on a biological electromyogram signal model generated by the human body. The output end of the impedance simulation module (2) is coupled to the measurement module (4). The impedance simulation module (2) is used to generate impedance parameters to simulate the impedance value generated by human blood flow on the signal. The anti-interference module (3) is electrically connected between the impedance simulation module (2) and the measurement module (4). The anti-interference module (3) is used to absorb transient pulse signals. The measurement module (4) is used to output hemodynamic parameter measurement data according to the ECG simulation signal.

6. An anti-interference fast absorption transient pulse system according to claim 5, characterized in that: The electrocardiogram (ECG) analog signal generation module (1) includes a DAC analog sub-module (11) and a main control sub-module (12). The main control sub-module (12) includes an analog ECG signal parameter output terminal and an impedance control terminal. The main control sub-module (12) outputs an analog ECG signal based on the biological electromyogram signal model generated by the human body. The impedance control terminal of the main control sub-module (12) is coupled to the impedance simulation module (2). The input terminal of the DAC analog sub-module (11) is coupled to the main control sub-module (12), and the output terminal of the DAC analog sub-module (11) is coupled to the impedance simulation module (2) to output an ECG analog signal to the impedance module.

7. An anti-interference fast absorption transient pulse system according to claim 6, characterized in that: The impedance simulation module (2) includes a switch sub-module (21) and a series resistor network sub-module (22). The input terminal of the switch sub-module (21) is coupled to the impedance control terminal of the main control sub-module (12), and the output terminal of the switch sub-module (21) is coupled to the series resistor network sub-module (22). The switch sub-module (21) is used to adjust the resistance value generated by the series resistor network sub-module (22). The output terminal of the series resistor network sub-module (22) is connected in series with the anti-interference module (3) and then coupled to the measurement module (4). The connection node between the series resistor network sub-module (22) and the switch sub-module (21) is coupled to the DAC analog sub-module (11).

8. A anti-interference fast absorption transient pulse system according to claim 7, characterized in that: The anti-interference module (3) includes a filtering sub-module (31) and several TVS tubes. One end of the filtering sub-module (31) is connected in series with the output terminal of the series resistor network sub-module (22), and the other end of the filtering sub-module (31) serves as a lead wire interface and is electrically connected to the measurement module (4). Several of the TVS tubes are respectively coupled within the filtering sub-module (31).

9. The anti-interference fast absorption transient pulse system according to claim 8, characterized in that: The filtering sub-module (31) includes two capacitors and an inductor. The two capacitors and the inductor are connected in series with each other. The connection node of one capacitor and the inductor is coupled to the series resistor network sub-module (22), and the connection node of the other capacitor and the inductor serves as the lead wire interface and is electrically connected to the measurement module (4). The connection node of the two capacitors is grounded.

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