Wearable equipment tool test method, tool test system and storage medium

Abstract

The invention discloses a wearable equipment tool testing method and system and a storage medium, and relates to the technical field of wearable equipment, and the wearable equipment tool testing method comprises the steps that according to a preset theoretical blood pressure value, a pulse signal and an electrocardiosignal are synchronously transmitted to preset wearable equipment; under the condition that rising edge triggering of the electrocardiosignal is detected, the heart sound signal is transmitted to the wearable device according to the theoretical blood pressure value, and the rising edge triggering means that the voltage value of the electrocardiosignal rises from being lower than a preset rising edge triggering threshold value to being higher than the rising edge triggering threshold value; acquiring a measured blood pressure value determined by the wearable device according to the received pulse signal, electrocardiosignal and heart sound signal; and determining a measurement score of the wearable device according to the theoretical blood pressure value and the measured blood pressure value. According to the method and the device, accurate and synchronous acquisition of the multi-modal physiological signals is realized by taking the electrocardio feature points as the triggering reference, and non-physiological system time delay interference is eliminated, so that the measurement and evaluation accuracy of the wearable equipment is improved.

Description

Technical Field

[0001] This application relates to the field of wearable device processing technology, and in particular to wearable device tooling testing methods, tooling testing systems and storage media. Background Technology

[0002] With the development of sensor technology and biomedical signal processing technology, wearable health monitoring devices have become an important technical means to achieve continuous and non-invasive monitoring of human physiological parameters. For example, by analyzing the physiological temporal relationship between multiple signals through wearable devices, key characteristic parameters such as pulse wave transit time can be extracted, and a blood pressure estimation model can be established to achieve continuous and non-invasive assessment of blood pressure.

[0003] Currently, in evaluating the accuracy of blood pressure measurement in wearable devices using multi-sensor signals, the time synchronization accuracy between sensor signals is a crucial prerequisite for ensuring reliable evaluation results. However, in actual multi-sensor signal transmission, differences in sensor hardware response characteristics inevitably introduce additional time delays between signals. This non-physiological time difference is directly superimposed on key parameters such as the actual pulse wave propagation time, causing the calculated delay value to deviate from its true physiological value. Consequently, the blood pressure estimation of the wearable device is based on a time benchmark with systematic errors, ultimately leading to uncontrollable errors in the accuracy evaluation of the wearable device and severely affecting the accuracy of the evaluation results.

[0004] The above content is only used to help understand the technical solution of this application and does not represent an admission that the above content is prior art. Summary of the Invention

[0005] The main objective of this application is to provide a tooling test method, tooling test system, and storage medium for wearable devices, aiming to solve the technical problem of how to improve the accuracy of blood pressure measurement and evaluation of wearable devices.

[0006] To achieve the above objectives, this application proposes a tooling testing method for wearable devices, the method comprising: Based on the preset theoretical blood pressure value, pulse signals and electrocardiogram signals are simultaneously transmitted to the preset wearable device; When the rising edge of the ECG signal is detected, a heart sound signal is transmitted to the wearable device according to the theoretical blood pressure value. The rising edge triggering refers to the voltage value of the ECG signal rising from below a preset rising edge triggering threshold to above the rising edge triggering threshold. The wearable device obtains the measured blood pressure value determined based on the received pulse signal, electrocardiogram signal, and heart sound signal; The measurement score of the wearable device is determined based on the theoretical blood pressure value and the measured blood pressure value.

[0007] In one embodiment, the step of transmitting a heart sound signal to the wearable device based on the theoretical blood pressure value when the rising edge of the electrocardiogram signal is detected includes: When the rising edge of the ECG signal is detected, a heart sound waveform is emitted by a heart sound signal generator, wherein the heart sound waveform is determined based on the theoretical blood pressure value; The heart sound waveform is converted into a heart sound signal using a passive speaker, and the heart sound signal is transmitted to the wearable device.

[0008] In one embodiment, the step of transmitting a heart sound waveform via a heart sound signal generator includes: Determine the average delay time between the electrocardiogram signal generator and the heart sound signal generator; The heart sound waveform pre-stored in the heart sound signal generator is shifted forward by the average delay time; The heart sound signal generator transmits the forward-shifted heart sound waveform.

[0009] In one embodiment, the step of simultaneously transmitting pulse signals and electrocardiogram signals to a preset wearable device based on a preset theoretical blood pressure value includes: Based on the theoretical blood pressure value, determine the theoretical pulse wave conduction time; Based on the theoretical pulse wave conduction time, the waveforms of the pulse signal and the electrocardiogram signal are adjusted so that the theoretical pulse wave conduction time and the waveform interval are equal, wherein the waveform interval is the time interval between the trough of the pulse signal and the peak of the R wave of the electrocardiogram signal. The adjusted pulse signal and the adjusted electrocardiogram signal are simultaneously transmitted to the wearable device.

[0010] In one embodiment, prior to the step of simultaneously transmitting pulse signals and electrocardiogram signals to a preset wearable device based on a preset theoretical blood pressure value, the method further includes: The software interface is displayed, which includes a blood pressure input box, an OK button, and a signal transmission button. In response to configuration actions performed on the blood pressure input field, determine the theoretical blood pressure value; In response to the trigger operation of the OK button, the ECG signal, pulse signal and heart sound signal are determined according to the theoretical blood pressure value, and the corresponding waveforms of the ECG signal, pulse signal and heart sound signal are displayed on the software interface; In response to a trigger operation on the signal transmission button, the steps of simultaneously transmitting pulse signals and electrocardiogram signals to a preset wearable device based on a preset theoretical blood pressure value, and subsequent steps, are performed.

[0011] In one embodiment, the step of determining the measurement score of the wearable device based on the theoretical blood pressure value and the measured blood pressure value includes: Calculate the absolute error between the theoretical blood pressure value and the measured blood pressure value; Based on the preset error range and scoring mapping relationship, the basic score corresponding to the absolute error value is determined; The variance of the fluctuation of multiple measured blood pressure values ​​output by the wearable device for the same theoretical blood pressure value within a preset time period is obtained. The measurement score is obtained by correcting the base score based on the variance of the fluctuation.

[0012] In one embodiment, after the step of determining the measurement score of the wearable device, the method further includes: If the measured score is lower than a preset score threshold, obtain the actual timestamps of the ECG signal, heart sound signal and pulse signal received by the wearable device; Based on the actual timestamps, the relative delay between each sensor channel of the wearable device is calculated, wherein the sensor channels include an electrocardiogram detection channel, a heart sound acquisition channel, and a pulse detection channel; Identify abnormal delay channels whose relative delay exceeds the preset synchronization accuracy requirement, and compensate and correct the abnormal delay channels.

[0013] In addition, to achieve the above objectives, this application also proposes a tooling testing system, which includes a controller, a pulse-ECG synchronization signal source, and a heart sound simulation device. The pulse-ECG synchronization signal source includes a pulse signal generator and an ECG signal generator. The ECG signal generator and the heart sound simulation device are connected to a preset wearable device, and the pulse signal generator is in contact with the wearable device. The pulse-ECG synchronization signal source is used to control the pulse signal generator and the ECG signal generator to synchronously transmit pulse signals and ECG signals to the wearable device according to a preset theoretical blood pressure value. The heart sound simulation device is used to transmit a heart sound signal to the wearable device based on the theoretical blood pressure value when the rising edge of the electrocardiogram signal is detected. The wearable device is used to determine the measured blood pressure value based on the received pulse signal, electrocardiogram signal, and heart sound signal; The controller is used to determine the measurement score of the wearable device based on the theoretical blood pressure value and the measured blood pressure value.

[0014] In one embodiment, the heart sound simulation device includes a heart sound signal generator and a passive speaker, wherein the heart sound signal generator is connected to the electrocardiogram signal generator, and the passive speaker is in contact with the wearable device; The heart sound signal generator is used to transmit a heart sound waveform when the rising edge of the electrocardiogram signal is detected, wherein the heart sound waveform is determined according to the theoretical blood pressure value; The passive speaker is used to convert the heart sound waveform into a heart sound signal and transmit the heart sound signal to the wearable device.

[0015] In addition, to achieve the above objectives, this application also proposes an electronic device, the device comprising: a memory, a processor, and a computer program stored in the memory and executable on the processor, the computer program being configured to implement the steps of the wearable device tooling testing method described above.

[0016] In addition, to achieve the above objectives, this application also proposes a storage medium, which is a computer-readable storage medium, on which a computer program is stored, and when the computer program is executed by a processor, it implements the steps of the wearable device tooling testing method described above.

[0017] In addition, to achieve the above objectives, this application also provides a computer program product, which includes a computer program that, when executed by a processor, implements the steps of the wearable device tooling testing method described above.

[0018] One or more technical solutions proposed in this application have at least the following technical effects: First, based on a preset theoretical blood pressure value, pulse signals and electrocardiogram (ECG) signals are synchronously transmitted to a preset wearable device, providing the wearable device with a known benchmark and an input source that conforms to physiological timing, thereby initiating the device evaluation process; then, when the rising edge of the ECG signal is detected, a heart sound signal is transmitted to the wearable device based on the theoretical blood pressure value. By setting a clear rising edge trigger threshold (i.e., the ECG signal rising from below the threshold to above the threshold), the ECG R wave (rising edge) is used as the anchor point for physiological synchronization, simulating the ECG-heart sound timing under real physiological conditions. This approach avoids non-physiological time differences caused by hardware response delays, ensuring that the time synchronization accuracy between the three signals conforms to physiological reality. Furthermore, it acquires the measured blood pressure value determined by the wearable device based on the received pulse, ECG, and heart sound signals. Because the wearable device's input signals have achieved high-precision time alignment, this measured blood pressure value can more accurately reflect core parameters such as pulse wave conduction time, eliminating non-physiological system delay interference. Then, based on the theoretical and measured blood pressure values, a measurement score for the wearable device is determined to objectively and accurately measure its actual measurement performance after eliminating signal delay errors. This application achieves precise synchronous acquisition of multimodal physiological signals by using ECG feature points as trigger references, improving the accuracy of the wearable device's input parameters. This results in a more accurate and reliable measurement score that reflects the device's true performance, thus improving the accuracy of wearable device measurement evaluation. Attached Figure Description

[0019] The accompanying drawings, which are incorporated in and form part of this specification, illustrate embodiments consistent with this application and, together with the description, serve to explain the principles of this application.

[0020] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, for those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0021] Figure 1 This is a flowchart illustrating an embodiment of the wearable device tooling testing method of this application. Figure 2 This is a flowchart illustrating Embodiment 2 of the wearable device tooling testing method of this application; Figure 3 This is a flowchart illustrating Embodiment 3 of the wearable device tooling testing method of this application; Figure 4 This is a schematic diagram of the tooling testing system structure provided in Embodiment 4 of this application; Figure 5 This is a technical roadmap for tooling testing of wearable devices provided in Embodiment 4 of this application.

[0022] Explanation of icon numbers: 1. Pulse signal generator; 2. Electrocardiogram signal generator; 3. Heart sound signal generator; 4. Passive speaker; 5. Wearable device; 6. First signal line; 7. Second signal line; 8. Third signal line.

[0023] The purpose, features, and advantages of this application will be further explained in conjunction with the embodiments and with reference to the accompanying drawings. Detailed Implementation

[0024] It should be understood that the specific embodiments described herein are merely illustrative of the technical solutions of this application and are not intended to limit this application.

[0025] To better understand the technical solution of this application, a detailed description will be provided below in conjunction with the accompanying drawings and specific implementation methods.

[0026] Currently, in evaluating the accuracy of blood pressure measurement using multi-sensor signals in wearable devices, the time synchronization accuracy between sensor signals is a crucial prerequisite for ensuring reliable evaluation results. However, in actual multi-sensor signal transmission, differences in sensor hardware response characteristics inevitably introduce additional time delays between signals. This non-physiological time difference is directly superimposed on key parameters such as the actual pulse wave propagation time, causing the calculated delay value to deviate from its true physiological value. Consequently, the blood pressure estimation of the wearable device is based on a time benchmark with systematic errors, ultimately leading to uncontrollable errors in the accuracy evaluation of the wearable device and severely affecting the accuracy of the evaluation results.

[0027] This application provides a solution. First, based on a preset theoretical blood pressure value, pulse and electrocardiogram (ECG) signals are synchronously transmitted to a preset wearable device, providing the wearable device with a known benchmark and physiologically consistent input source, thereby initiating the device evaluation process. Then, upon detecting a rising edge trigger of the ECG signal, a heart sound signal is transmitted to the wearable device based on the theoretical blood pressure value. By setting a specific rising edge trigger threshold (i.e., the ECG signal rising from below the threshold to above the threshold), the ECG R wave (rising edge) is used as an anchor point for physiological synchronization, simulating the ECG-heart sound temporal relationship under real physiological conditions, while avoiding… The non-physiological time difference caused by hardware response delay ensures that the time synchronization accuracy between the three signals conforms to physiological reality. Furthermore, the wearable device obtains the measured blood pressure value determined by the received pulse signal, ECG signal, and heart sound signal. Because the wearable device's input signals have achieved high-precision time alignment, this measured blood pressure value can more accurately reflect core parameters such as pulse wave conduction time, eliminating non-physiological system delay interference. Subsequently, based on the theoretical blood pressure value and the measured blood pressure value, a measurement score for the wearable device is determined to objectively and accurately measure its actual measurement performance after eliminating signal delay errors. This application achieves precise synchronous acquisition of multimodal physiological signals by using ECG feature points as trigger references, improving the accuracy of the wearable device's input parameters. This results in a more accurate and reliable measurement score that reflects the device's true performance, thus improving the accuracy of wearable device measurement evaluation.

[0028] It should be noted that the executing entity in this embodiment can be an electronic device with data processing, network communication and program running functions, such as a tablet computer, personal computer, mobile phone, etc.; the electronic device can control the transmission of physiological simulation signals such as electrocardiogram signals, pulse signals, and heart sound signals to the wearable device, and can also obtain the blood pressure value calculated and output by the wearable device based on the above-mentioned multiple physiological simulation signals, and evaluate and analyze it.

[0029] Wearable devices refer to a type of device to be evaluated, equipped with multiple physiological signal acquisition interfaces (such as electrode interfaces, electrical sensor interfaces, etc.), capable of receiving multiple externally input physiological analog signals and outputting calculated blood pressure measurements. Specific product forms include, but are not limited to, smart bracelets, smartwatches, smart rings, and smart chest patches.

[0030] Based on this, embodiments of this application provide a tooling testing method for wearable devices, referring to... Figure 1 , Figure 1 This is a flowchart illustrating the first embodiment of the wearable device tooling testing method of this application.

[0031] In this embodiment, the wearable device tooling testing method includes steps S10 to S40: Step S10: Based on the preset theoretical blood pressure value, simultaneously transmit pulse signal and electrocardiogram signal to the preset wearable device; Theoretical blood pressure refers to blood pressure data in the form of numerical pairs (systolic pressure / diastolic pressure), used to compare and analyze with subsequent actual measured or calculated blood pressure values ​​to evaluate the measurement accuracy of wearable devices or to perform other related calculations.

[0032] Pulse signal refers to the peripheral arterial pulsation signal collected by photoplethysmography (PPG), pressure sensor, etc., which reflects the changes in blood volume caused by the heart pumping blood. Its periodic trough point usually corresponds to the start of ventricular diastole and can be used to calibrate the end point of pulse wave transit time (PWTT). PPG signal refers to photoplethysmography pulse wave signal (pulse signal).

[0033] Electrocardiogram (ECG) refers to the electrical activity signal of the heart collected by sensors such as ECG surface electrodes. It reflects the depolarization and repolarization process of the myocardium. Its typical waveforms include the P wave, QRS complex (including R wave), and T wave. Among them, the R wave is the positive wave with the highest amplitude in the QRS complex. It has the most significant amplitude and slope characteristics and is often used as a reference point for physiological timing to calibrate the onset time of cardiac electrical activity.

[0034] For example, waveform parameters (such as heart rate, amplitude, waveform morphology, etc.) of pulse signals and electrocardiogram signals that match the current theoretical blood pressure value (i.e., the same user at the same time) can be found from a large database of pre-collected physiological signals containing multiple sets of blood pressure values ​​and corresponding physiological signals; then, based on the waveform parameters, the corresponding pulse signals and electrocardiogram signals can be synchronously transmitted to the wearable device.

[0035] For example, precise synchronous transmission of the two signals can also be achieved through an integrated PPG / ECG signal synchronization generator (such as the AEGG100 multi-channel physiological signal simulator). This device uses the same clock source internally, ensuring that the time difference between the two signals when they leave the transmission port is within the nanosecond range.

[0036] Optionally, a main controller can simultaneously send start commands to independent pulse signal generators and ECG signal generators, and connect the two generators through a hardware trigger line to ensure that they start waveform output simultaneously when they receive the rising edge of the same pulse signal, thereby realizing the synchronous transmission of PPG and ECG signals.

[0037] In one possible implementation, prior to step S10, the method further includes: The software interface is displayed, which includes a blood pressure input box, an OK button, and a signal transmission button. In response to configuration actions performed on the blood pressure input field, determine the theoretical blood pressure value; In response to the trigger operation of the OK button, the ECG signal, pulse signal and heart sound signal are determined according to the theoretical blood pressure value, and the corresponding waveforms of the ECG signal, pulse signal and heart sound signal are displayed on the software interface; In response to a trigger operation on the signal transmission button, step S10 and subsequent steps are executed.

[0038] It should be noted that the software interface refers to the graphical user interface (GUI) that runs on electronic devices and is used for human-computer interaction with testers; this interface integrates functions such as test process control, parameter setting, and real-time status display.

[0039] The blood pressure input box is an area in the software interface where users can input text or numbers. Users can input or select the theoretical blood pressure value required for this test in this area using the keyboard or mouse, such as systolic pressure 120 and diastolic pressure 80.

[0040] The "OK" button refers to a clickable graphical control in the software interface (such as a button labeled "OK" or "Load Waveform"). After the user clicks the "OK" button, the electronic device will read the value in the blood pressure input box and retrieve or generate the corresponding ECG, pulse, and heart sound waveform data from the preset waveform library based on the value, and display the preview on the software interface.

[0041] The signal transmission button refers to another clickable graphical control in the software interface (such as a button labeled "Start Test" or "Transmit Signal"). After the user clicks the signal transmission button, the electronic device will officially start the test process, that is, start transmitting signals to the wearable device according to the preset program.

[0042] For example, the electronic device displays a software interface. The tester enters "135 / 85" in the blood pressure input box and clicks the "OK" button. The interface immediately displays simulated ECG, pulse, and heart sound waveforms with slightly higher amplitudes, corresponding to mild hypertension. Then, after confirming the waveforms are correct, the tester clicks the "Start Test" button. The electronic device then synchronously transmits ECG and pulse signals to the connected wearable device via a signal generator.

[0043] In this embodiment, by providing a visual software interface, testers can intuitively set test parameters, preview test signals, and control the start and stop of tests, which simplifies the complexity of test operations and improves the automation level of the test process.

[0044] Step S20: When the rising edge of the electrocardiogram signal is detected, a heart sound signal is transmitted to the wearable device according to the theoretical blood pressure value. Rising edge triggering refers to the voltage value of the electrocardiogram signal rising from below the preset rising edge triggering threshold to above the rising edge triggering threshold.

[0045] Rising edge triggering is a signal detection mechanism that presets a rising edge triggering threshold for the electrocardiogram (ECG) signal. When the voltage value of the ECG signal gradually rises from below the threshold and exceeds the threshold, it is determined to be a rising edge triggering, generating a single-cycle effective trigger pulse signal to drive the synchronous initiation of subsequent events (such as the transmission of heart sound signals).

[0046] The rising edge trigger threshold is a preset, fixed reference voltage value. Its setting needs to take into account the typical amplitude of the R wave in the ECG signal and the baseline noise level. It is usually set slightly higher than the maximum value of the ECG signal baseline noise to ensure that the rising edge of the R wave in each cardiac cycle can be captured stably and accurately, while avoiding false triggering caused by electromyographic interference, power frequency noise, etc.

[0047] Phonocardiogram (PCG) refers to the acoustic signal collected by sensors such as microphones and accelerometers, which is generated by mechanical vibrations such as the closure of heart valves and blood flow turbulence. It mainly includes the first heart sound (S1, corresponding to the closure of the mitral and tricuspid valves) and the second heart sound (S2, corresponding to the closure of the aortic and pulmonary valves). Its internal multi-peak structure contains information on valvular dynamics and cardiac function status.

[0048] For example, during the process of searching for the waveform parameters of pulse signals and electrocardiogram signals, the waveform parameters of the heart sound signal of the same user at the same time corresponding to the current theoretical blood pressure value can be searched simultaneously from the pre-collected physiological signal database. Furthermore, during the real-time monitoring of the electrocardiogram signal, once it is detected that the voltage value changes from below the preset rising edge trigger threshold to above the threshold (i.e., it is determined that an R wave is detected), the heart sound signal is immediately transmitted to the wearable device according to the found heart sound signal waveform parameters.

[0049] Understandably, by using the rising edge triggering mechanism, the transmission of heart sound signals is locked at the hardware level with the most representative R wave (the start of cardiac electrical activity) in the electrocardiogram signal, thereby ensuring that the heart sound signals are strictly aligned with the actual electromechanical delay of the heart in timing, providing wearable devices with the closest physiological signal input to reality.

[0050] In one feasible implementation, step S20 includes: Step S21: When the rising edge of the electrocardiogram signal is detected, a heart sound waveform is emitted through the heart sound signal generator, wherein the heart sound waveform is determined according to the theoretical blood pressure value; A heart sound signal generator is an electronic instrument used to generate electrical signal waveforms that simulate the mechanical activity of the heart. It typically includes a memory that stores digital samples of various heart sound waveforms and a digital-to-analog converter (DAC) that converts the digital samples into continuous analog voltage signals.

[0051] Heart sound waveform refers to a time-varying voltage signal, which is the electrical representation of the sound of the heart's mechanical activity, containing the complete vibration envelope of S1 and S2; its corresponding waveform characteristic parameters (such as dominant frequency, harmonic components, duration, rise / fall slope, etc.) are determined according to the current theoretical blood pressure value and a certain predefined mapping rule.

[0052] For example, a heart sound waveform matching the theoretical blood pressure value can be obtained by looking up a pre-stored heart sound-blood pressure mapping table; alternatively, a physical model formula can be used to dynamically calculate and generate the corresponding heart sound waveform parameters based on the theoretical blood pressure value.

[0053] Step S22: The heart sound waveform is converted into a heart sound signal using a passive speaker, and the heart sound signal is transmitted to the wearable device.

[0054] A passive acoustic transducer is an acoustic transducer without a built-in power amplifier. It typically consists of a permanent magnet, a voice coil, and a diaphragm. It relies on an externally input analog audio current to drive the voice coil to experience a force in a magnetic field, which in turn causes the diaphragm to vibrate, converting electrical energy into mechanical energy in the form of sound waves. Because it has no internal active amplifier circuit, the signal path is the shortest, allowing it to reproduce the details of the original heart sound waveform with the highest fidelity.

[0055] For example, the analog voltage signal output by the heart sound signal generator is driven by a simple audio power amplifier (which can be regarded as part of the heart sound signal generator or a separate unit) to drive a passive speaker to emit sound waves. These sound waves are received by the heart sound acquisition sensor (such as a microphone) on the wearable device, thereby enabling the transmission of the heart sound signal to the wearable device.

[0056] In this embodiment, a heart sound waveform matching the theoretical blood pressure value is generated by a heart sound signal generator, and then converted into a real physical sound wave by a passive speaker and transmitted to the wearable device. This achieves a complete and high-fidelity injection from electrical signal to physical acoustic signal, enabling the wearable device to effectively pick up the heart sound signal.

[0057] In one feasible implementation, step S21 includes: Step S211: Determine the average delay time between the ECG signal generator and the heart sound signal generator; The average delay time refers to the average time difference between the generation of an electrocardiogram (ECG) signal by the ECG signal generator and the generation of a heart sound signal by the heart sound signal generator based on the ECG signal. It is calculated through multiple measurements and statistical calculations and represents the fixed delay inherent in the electronic device that needs to be compensated for.

[0058] Step S212: Shift the pre-stored heart sound waveform in the heart sound signal generator forward by the average delay time; Step S213: The forward-shifted heart sound waveform is transmitted through the heart sound signal generator.

[0059] Forward shift refers to a negative time axis adjustment operation performed on the starting point of reading the waveform sample sequence in the digital waveform data buffer of a heart sound signal generator.

[0060] For example, the average delay time is obtained by calculating the time difference between the electrocardiogram (ECG) signal and the heart sound signal over a period of time (e.g., 100 heartbeat cycles). Then, based on this average delay time, the starting point of the heart sound waveform sample sequence corresponding to the theoretical blood pressure value is shifted forward by a corresponding time length in the waveform data buffer of the heart sound signal generator. Finally, the shifted heart sound waveform is transmitted through the heart sound signal generator to compensate for the delay between the two signal generators, ensuring accurate time synchronization between the heart sound signal and the ECG signal. For instance, if the measured average delay time is 400 microseconds and the heart sound waveform sampling rate is 10kHz (i.e., one sampling point every 100 microseconds), when the R-wave trigger event occurs, the heart sound signal generator no longer reads and transmits the heart sound waveform from address 0, but directly from address 4. This ensures that after the inherent 400 microsecond delay in its hardware path, the actual starting point of the heart sound waveform is precisely aligned with the ECG R-wave on the physical time axis.

[0061] In this embodiment, active compensation is achieved by shifting the heart sound waveform forward, reducing the inherent system delay caused by hardware differences in the two signal transmission paths of ECG and heart sound. This ensures that the two signals that finally reach the wearable device are ideally aligned in physical time, improving the accuracy of parameters such as the ECG-heart sound interval measured by the wearable device in the subsequent measurement, reducing the impact of non-device factors on blood pressure measurement, and thus improving the accuracy of blood pressure measurement assessment.

[0062] Step S30: Obtain the measured blood pressure value determined by the wearable device based on the received pulse signal, electrocardiogram signal and heart sound signal; For example, after receiving pulse signals, electrocardiogram (ECG) signals, and heart sound signals, the wearable device identifies feature points such as the R wave of the ECG signal, the S1 wave of the heart sound signal, and the trough of the pulse signal through an internal algorithm, and determines the positioning time point corresponding to each feature point; then, based on the positioning time point of each feature point, it calculates the time interval from the R wave to S1 (i.e., the ECG-heart sound interval) and the time interval from the heart sound S1 to the trough of the pulse wave (i.e., the pulse wave conduction time), and calculates the measured blood pressure value by combining it with a preset blood pressure calculation formula.

[0063] For example, wearable devices can also input the location time points of each feature point into a pre-trained blood pressure estimation model (such as a model based on linear regression or neural networks) and output the measured blood pressure value.

[0064] Step S40: Determine the measurement score of the wearable device based on the theoretical blood pressure value and the measured blood pressure value.

[0065] Measurement score refers to a comprehensive index used to quantitatively evaluate the blood pressure measurement performance of wearable devices. It can be a numerical value or a grade, and this implementation method does not make specific limitations on it.

[0066] For example, the difference between the theoretical blood pressure value and the measured blood pressure value can be calculated. If the absolute value of the difference is less than 5 mmHg, it is rated as "excellent"; if it is between 5 and 10 mmHg, it is rated as "good"; if it is greater than 10 mmHg, it is rated as "poor".

[0067] This embodiment provides a tooling testing method for wearable devices. By realizing the synchronous transmission of multimodal physiological signals (ECG, pulse, heart sounds) based on theoretical blood pressure and using the ECG R wave as the physiological synchronization anchor point, it provides wearable devices with highly simulated and time-precise test signals, reduces system errors introduced by differences in the hardware of the test equipment itself, realizes accurate evaluation of the measurement results of wearable devices, and effectively improves the testing accuracy of the blood pressure measurement function of wearable devices.

[0068] Based on the first embodiment of this application, in the second embodiment of this application, the same or similar content as the first embodiment described above can be referred to the above description, and will not be repeated hereafter.

[0069] Please refer to Figure 2 , Figure 2 This is a flowchart illustrating the second embodiment of the wearable device tooling testing method of this application. Based on this, step S10 includes: Step S11: Determine the theoretical pulse wave conduction time based on the theoretical blood pressure value; Pulse wave conduction time (PWTT) refers to the time required for a pulse wave generated by cardiac electrical activity (usually calibrated by the R wave in an electrocardiogram) to travel to distal parts of the body (such as fingers and wrists). It is generally negatively correlated with blood pressure. The theoretical pulse wave conduction time (PWTT) is the PWTT value that matches the theoretical blood pressure value. It can be calculated based on a pre-existing mathematical conversion model between pulse wave conduction time and blood pressure.

[0070] Step S12: Adjust the waveforms of the pulse signal and the electrocardiogram signal according to the theoretical pulse wave conduction time so that the theoretical pulse wave conduction time and the waveform interval are equal. Waveform interval refers to the time difference between the location point corresponding to the trough of the pulse signal and the location point corresponding to the peak of the R wave in the electrocardiogram signal.

[0071] For example, by adjusting the signal generation parameters (such as signal start time, period, etc.) of the pulse signal generator and the electrocardiogram (ECG) signal generator, the time interval between the trough of the pulse signal and the peak of the R-wave in the ECG signal can be made equal to the calculated theoretical pulse wave conduction time. For instance, if the theoretical pulse wave conduction time is 200 ms, by adjusting the signal generation parameters, the trough of the pulse signal can be made to appear 200 ms after the peak of the R-wave in the ECG signal.

[0072] Step S13: Simultaneously transmit the adjusted pulse signal and the adjusted electrocardiogram signal to the wearable device.

[0073] For example, the electronic device simultaneously sends trigger signals to both the pulse signal generator and the electrocardiogram (ECG) signal generator, causing them to synchronously transmit pulse and ECG signals to the wearable device according to adjusted signal generation parameters.

[0074] In this embodiment, by inversely calculating the theoretical PWTT based on the theoretical blood pressure value, and precisely adjusting the relative time interval between the two signal waveforms in the transmitted signal with this as the target, the signal transmitted to the wearable device itself carries physiological timing information that strictly corresponds to the theoretical blood pressure value. This ensures that the input signal to the wearable device is accurate, thereby enabling the evaluation of the signal acquisition and blood pressure value analysis effect of the wearable device itself, and improving the evaluation accuracy of blood pressure measurement by the wearable device.

[0075] In one feasible implementation, the tooling testing method for wearable devices further includes: Step S01: Obtain a blood pressure test sequence containing multiple different theoretical blood pressure values, wherein the blood pressure test sequence includes at least a low blood pressure range, a normal blood pressure range, and a high blood pressure range; A blood pressure test sequence is an ordered set of data containing multiple different theoretical blood pressure values; by comprehensively covering various blood pressure states that may occur in the human body, it evaluates the measurement performance of wearable devices across the entire measurement range.

[0076] Step S02 involves performing the step of synchronously transmitting pulse signals and electrocardiogram signals to a preset wearable device for each theoretical blood pressure value in the blood pressure test sequence, and subsequent steps.

[0077] For example, the electronic device automatically loads the acquired blood pressure test sequence and performs steps S10 to S40 for each theoretical blood pressure value to obtain a measurement score until all blood pressure values ​​in the blood pressure test sequence have been tested, thus obtaining a set of performance scores for the wearable device at different blood pressure levels.

[0078] In this embodiment, by introducing a blood pressure test sequence covering the entire range, the single-point test is expanded into a comprehensive evaluation of multiple points and the entire range. This allows the final test results to more comprehensively reveal the measurement accuracy of wearable devices in different blood pressure ranges and potential algorithm defects, thereby improving the comprehensiveness of the evaluation of blood pressure measurement of wearable devices and providing richer data support for device performance optimization.

[0079] Based on the first and / or second embodiments of this application, in the third embodiment of this application, the contents that are the same as or similar to those in the first and second embodiments described above can be referred to the above description and will not be repeated hereafter.

[0080] Please refer to Figure 3 , Figure 3 This is a flowchart illustrating the third embodiment of the wearable device tooling testing method of this application. Based on this, step S40 includes: Step S41: Calculate the absolute error between the theoretical blood pressure value and the measured blood pressure value; The absolute error value refers to the absolute value of the difference between the theoretical blood pressure value and the measured blood pressure value. Considering that blood pressure is usually expressed in two values, systolic pressure and diastolic pressure, this absolute error value can be the absolute error of systolic pressure and the absolute error of diastolic pressure, or it can be a combination of the two (such as root mean square error). This implementation method does not impose specific limitations on this.

[0081] Step S42: Determine the base score corresponding to the absolute error value based on the preset error range and scoring mapping relationship; The error range and score mapping relationship refers to a predefined rule table that maps different absolute error ranges to different base scores.

[0082] The baseline score is an initial score determined based on the accuracy of a single measurement (i.e., the absolute error between the measured value and the theoretical value).

[0083] For example, if the absolute error values ​​include systolic blood pressure error less than or equal to 3 mmHg and diastolic blood pressure error less than or equal to 2 mmHg, the corresponding base score is 100 points according to the preset error range and scoring mapping relationship; if both are between 3 and 5 mmHg, the corresponding base score is 80 points.

[0084] Step S43: Obtain the variance of the fluctuation of multiple measured blood pressure values ​​output by the wearable device for the same theoretical blood pressure value within a preset time period; Variance fluctuation refers to the degree of dispersion among multiple consecutive blood pressure measurements output by a wearable device under the same test conditions (same theoretical blood pressure value, same signal input); the larger the variance fluctuation, the more unstable the measurement results of the device.

[0085] For example, the measured blood pressure values ​​output by the wearable device for the same theoretical blood pressure value within 5 minutes can be obtained, and the variance of this set of data can be calculated to obtain the fluctuation variance.

[0086] Step S44: Correct the base score based on the variance of the fluctuation to obtain the measurement score.

[0087] For example, a correction factor can be determined based on the variance of fluctuation, and the correction factor can be multiplied by the base score to obtain the final measurement score of the wearable device. The larger the variance of fluctuation, the smaller the corresponding correction factor and the smaller the corresponding measurement score.

[0088] In this embodiment, by introducing a two-level scoring mechanism of baseline score and fluctuation variance correction, the final measurement score not only reflects the accuracy of the device measurement, but also its measurement stability, thus achieving a comprehensive and accurate evaluation of the blood pressure measurement effect of wearable devices.

[0089] In one possible implementation, after step S40, the method further includes: Step S50: If the measured score is lower than the preset score threshold, obtain the actual timestamps of the ECG signal, heart sound signal and pulse signal received by the wearable device. Actual timestamps refer to the precise moments when wearable devices actually detect electrocardiogram (ECG), heart sound, and pulse signals through their sensor channels, as recorded internally by the device. These timestamps are typically based on the wearable device's local clock.

[0090] Step S60: Calculate the relative delay between each sensor channel of the wearable device based on each actual timestamp, wherein the sensor channels include an ECG detection channel, a heart sound acquisition channel, and a pulse detection channel; Relative delay refers to the time difference between signals received by different sensor channels, reflecting the time synchronization of each sensor channel during signal acquisition and transmission. Since the wearable device tooling test method of this application has already achieved time synchronization during signal transmission, this relative delay originates from the signal acquisition process of the wearable device itself.

[0091] For example, the relative delay between the ECG detection channel and the heart sound acquisition channel is calculated based on the difference between the actual timestamps corresponding to the ECG signal and the heart sound signal; similarly, the relative delay between the ECG detection channel and the pulse detection channel, as well as the relative delay between the heart sound acquisition channel and the pulse detection channel, are calculated.

[0092] Step S70: Identify abnormal delay channels whose relative delay exceeds the preset synchronization accuracy requirement, and compensate and correct the abnormal delay channels.

[0093] Synchronization accuracy requirements refer to the maximum allowable relative delay between each sensor channel, which can be set according to the functional requirements and testing standards of the wearable device.

[0094] For example, the calculated relative delays between channels are compared with preset synchronization accuracy requirements. If the relative delays of two channels exceed the synchronization accuracy requirements, these two channels are identified as abnormal delay channels. For abnormal delay channels, time compensation correction can be performed on the signal through software algorithms during the blood pressure value estimation process of the wearable device. For example, based on the magnitude of the relative delay, the signal of the abnormal channel can be processed earlier or later during signal processing to make it synchronized with the signals of other channels in time.

[0095] For example, the delay of an abnormally delayed channel can also be reduced physically by adjusting the filter parameters or the sampling clock phase.

[0096] In this embodiment, by obtaining the actual timestamp, calculating the relative delay, and compensating for abnormal channels, not only is the accurate scoring of the blood pressure measurement effect of wearable devices achieved, but also the optimization of unqualified devices is further realized, which is conducive to improving the product yield of wearable devices.

[0097] Based on the first, second, and / or third embodiments of this application, this application proposes a tooling testing system according to a fourth embodiment. In this fourth embodiment, content that is the same as or similar to that in embodiments one, two, and three above can be referred to the above description and will not be repeated hereafter.

[0098] In this embodiment, the tooling testing system includes a controller, a pulse-ECG synchronization signal source, and a heart sound simulation device. The pulse-ECG synchronization signal source includes a pulse signal generator and an ECG signal generator. The ECG signal generator and the heart sound simulation device are connected to a preset wearable device, and the pulse signal generator is in contact with the wearable device. The pulse-ECG synchronization signal source is used to control the pulse signal generator and the ECG signal generator to synchronously transmit pulse signals and ECG signals to the wearable device according to a preset theoretical blood pressure value. The heart sound simulation device is used to transmit a heart sound signal to the wearable device based on the theoretical blood pressure value when the rising edge of the electrocardiogram signal is detected. The wearable device is used to determine the measured blood pressure value based on the received pulse signal, electrocardiogram signal, and heart sound signal; The controller is used to determine the measurement score of the wearable device based on the theoretical blood pressure value and the measured blood pressure value.

[0099] It should be noted that the pulse-ECG synchronized signal source refers to a multi-functional signal generation unit that integrates a pulse signal generator and an ECG signal generator. It possesses a unified clock source and hardware triggering mechanism, ensuring that the sampling clocks of the two signals are from the same source and are phase-aligned. It supports the generation and synchronous transmission control of physiological signals based on theoretical blood pressure values. Specifically, the pulse signal generator is an electronic module used to generate simulated human PPG signals, and the ECG signal generator is an electronic module used to generate simulated human ECG signals.

[0100] A heart sound simulation device is an electronic unit that can generate and emit heart sound signals.

[0101] The controller is the central control unit of the entire tooling testing system. It is responsible for executing the testing process, such as communicating with each signal generator, setting waveform parameters, communicating with wearable devices to read measurement results, performing calculations and analysis, and outputting scores.

[0102] In one feasible implementation, the heart sound simulation device includes a heart sound signal generator and a passive speaker, wherein the heart sound signal generator is connected to the electrocardiogram signal generator and the passive speaker is in contact with the wearable device; The heart sound signal generator is used to transmit a heart sound waveform when the rising edge of the electrocardiogram signal is detected, wherein the heart sound waveform is determined according to the theoretical blood pressure value; The passive speaker is used to convert the heart sound waveform into a heart sound signal and transmit the heart sound signal to the wearable device.

[0103] It should be noted that the method for transmitting heart sound signals through a heart sound signal generator and a passive speaker is the same as the process of steps S21 to S22 in the first embodiment above, so it will not be repeated here.

[0104] For example, please refer to Figure 4 , Figure 4 This is a schematic diagram of the tooling testing system provided in this application. The tooling testing system includes a controller, a pulse-ECG synchronous signal source (including a pulse signal generator 1 and an ECG signal generator 2), and a heart sound simulation device (including a heart sound signal generator 3 and a passive speaker 4). The ECG signal generator 2 is connected to a wearable device 5 via a first signal line 6 to transmit an ECG signal to the wearable device 5 based on a theoretical blood pressure value. The ECG signal generator 2 is also connected to the heart sound signal generator 3 via a second signal line 7 to synchronously transmit an ECG signal to the heart sound signal generator 3. Furthermore, the heart sound signal generator 3 can generate heart sounds based on a theoretical blood pressure value upon detecting the rising edge of the ECG signal. The waveform is transmitted to the passive speaker 4 via the third signal line 8. The passive speaker 4 then converts the waveform into a heart sound signal, and since it is in direct contact with the wearable device 5, it can transmit the heart sound signal to the wearable device 5. At the same time as the ECG signal generator 2 transmits the ECG signal, the pulse signal generator 1 also transmits the pulse signal to the wearable device 5 based on the theoretical blood pressure value. The wearable device 5 can then calculate the measured blood pressure value based on the received ECG signal, pulse signal, and heart sound signal. The controller can then obtain the measured blood pressure value generated by the wearable device 5 and compare it with the theoretical blood pressure value to determine the measurement score of the wearable device 5.

[0105] In one feasible implementation, the controller is configured to determine the average delay time between the electrocardiogram signal generator and the heart sound signal generator, and shift the heart sound waveform pre-stored in the heart sound signal generator forward by the average delay time; The heart sound signal generator is used to transmit the forward-shifted heart sound waveform.

[0106] The specific implementation steps of the controller can be referred to the specific implementation process of steps S211~S212 in the first embodiment, which will not be repeated here.

[0107] For example, please refer to Figure 5 , Figure 5A test technology roadmap for wearable device tooling is provided. First, an ECG generator and a PCG generator are controlled to synchronously transmit ECG and PPG signals to the wearable device, where the ECG and PPG signals are determined based on preset theoretical blood pressure values. Simultaneously, by detecting the rising edge trigger of the ECG signal—that is, when the voltage value of the ECG signal changes from below a preset rising edge trigger threshold to above that threshold—the PCG generator is controlled to transmit a heart sound waveform based on the preset theoretical blood pressure value. This waveform is then converted to a passive acoustic signal and transmitted to the wearable device as a PCG signal. During the transmission of the PCG signal, delay compensation can be performed based on the average delay time between the ECG and PCG generators. Specifically, the waveform sequence of the heart sound waveform generated by the PCG generator is shifted forward based on the average delay time, allowing the wearable device to receive synchronized ECG, PPG, and PCG signals. The wearable device then calculates its blood pressure value. Finally, the measured blood pressure value calculated by the wearable device is compared with the aforementioned theoretical blood pressure value to evaluate the blood pressure measurement effectiveness of the wearable device.

[0108] In one feasible implementation, the controller is configured to determine the theoretical pulse wave conduction time based on the theoretical blood pressure value; and adjust the waveforms of the pulse signal and the electrocardiogram signal based on the theoretical pulse wave conduction time so that the theoretical pulse wave conduction time is equal to the waveform interval, wherein the waveform interval is the time interval between the trough of the pulse signal and the peak of the R wave of the electrocardiogram signal. The pulse-ECG synchronization signal source is used to synchronously transmit the adjusted pulse signal and the adjusted ECG signal to the wearable device.

[0109] In one feasible implementation, the tooling testing system is used to display a software interface, wherein the software interface includes a blood pressure input box, a confirm button, and a signal transmission button; in response to a configuration operation on the blood pressure input box, a theoretical blood pressure value is determined; in response to a trigger operation on the confirm button, an electrocardiogram (ECG) signal, a pulse signal, and a heart sound signal are determined based on the theoretical blood pressure value, and the waveforms corresponding to the ECG signal, pulse signal, and heart sound signal are displayed on the software interface; in response to a trigger operation on the signal transmission button, the system executes the step of synchronously transmitting the pulse signal and ECG signal to a preset wearable device based on a preset theoretical blood pressure value, and subsequent steps.

[0110] In one feasible implementation, the controller is configured to calculate the absolute error between the theoretical blood pressure value and the measured blood pressure value; determine the base score corresponding to the absolute error value according to a preset error interval and scoring mapping relationship; obtain the fluctuation variance of multiple measured blood pressure values ​​output by the wearable device for the same theoretical blood pressure value within a preset time period; and correct the base score according to the fluctuation variance to obtain the measurement score.

[0111] In one feasible implementation, the controller is configured to, when the measured score is lower than a preset scoring threshold, acquire the actual timestamps of the ECG signal, the heart sound signal, and the pulse signal received by the wearable device; calculate the relative delay between each sensor channel of the wearable device based on each actual timestamp, wherein the sensor channel includes an ECG detection channel, a heart sound acquisition channel, and a pulse detection channel; identify abnormal delay channels whose relative delay exceeds a preset synchronization accuracy requirement, and compensate and correct the abnormal delay channels.

[0112] This application provides a computer-readable storage medium having computer-readable program instructions (i.e., a computer program) stored thereon, which are used to execute the wearable device tooling testing method in the above embodiments.

[0113] The computer-readable storage medium provided in this application embodiment may be, for example, a USB flash drive, but is not limited to, electrical, magnetic, optical, electromagnetic, infrared, or semiconductor systems or devices, or any combination thereof. More specific examples of computer-readable storage media may include, but are not limited to: electrical connections having one or more wires, portable computer disks, hard disks, random access memory (RAM), read-only memory (ROM), erasable programmable read-only memory (EPROM or flash memory), optical fibers, portable compact disk read-only memory (CD-ROM), optical storage devices, magnetic storage devices, or any suitable combination thereof. In this embodiment, the computer-readable storage medium may be any tangible medium containing or storing a program that can be used by or in conjunction with an instruction execution system or device. The program code contained on the computer-readable storage medium may be transmitted using any suitable medium, including but not limited to: wires, optical cables, RF (Radio Frequency), etc., or any suitable combination thereof.

[0114] The aforementioned computer-readable storage medium may be included in an electronic device or may exist independently without being assembled into an electronic device.

[0115] The aforementioned computer-readable storage medium carries one or more programs that, when executed by an electronic device, cause the electronic device to: synchronously transmit pulse signals and electrocardiogram (ECG) signals to a preset wearable device based on a preset theoretical blood pressure value; transmit heart sound signals to the wearable device based on the theoretical blood pressure value when a rising edge trigger is detected in the ECG signal, wherein rising edge trigger refers to the voltage value of the ECG signal rising from below a preset rising edge trigger threshold to above the rising edge trigger threshold; acquire the measured blood pressure value determined by the wearable device based on the received pulse signal, ECG signal, and heart sound signals; and determine a measurement score for the wearable device based on the theoretical blood pressure value and the measured blood pressure value.

[0116] Computer program code for performing the operations of this application can be written in one or more programming languages ​​or a combination thereof, including object-oriented programming languages ​​such as Java, Smalltalk, and C++, and conventional procedural programming languages ​​such as the "C" language or similar programming languages. The program code can be executed entirely on the user's computer, partially on the user's computer, as a standalone software package, partially on the user's computer and partially on a remote computer, or entirely on a remote computer or server. In cases involving remote computers, the remote computer can be connected to the user's computer via any type of network—including a Local Area Network (LAN) or a Wide Area Network (WAN)—or can be connected to an external computer (e.g., via the Internet using an Internet service provider).

[0117] The flowcharts and block diagrams in the accompanying drawings illustrate the architecture, functionality, and operation of possible implementations of systems, methods, and computer program products according to various embodiments of this application. In this regard, each block in a flowchart or block diagram may represent a module, segment, or portion of code containing one or more executable instructions for implementing a specified logical function. It should also be noted that in some alternative implementations, the functions indicated in the blocks may occur in a different order than those indicated in the drawings. For example, two consecutively indicated blocks may actually be executed substantially in parallel, and they may sometimes be executed in reverse order, depending on the functions involved. It should also be noted that each block in the block diagrams and / or flowcharts, and combinations of blocks in the block diagrams and / or flowcharts, can be implemented using a dedicated hardware-based system that performs the specified function or operation, or using a combination of dedicated hardware and computer instructions.

[0118] The modules described in the embodiments of this application can be implemented in software or hardware. The names of the modules do not necessarily limit the functionality of the unit itself.

[0119] The readable storage medium provided in this application is a computer-readable storage medium. This computer-readable storage medium stores computer-readable program instructions (i.e., a computer program) for executing the aforementioned wearable device tooling testing method, and can solve the technical problem of how to improve the accuracy of blood pressure measurement and evaluation using wearable devices. Compared with the prior art, the beneficial effects of the computer-readable storage medium provided in this application are the same as the beneficial effects of the wearable device tooling testing method provided in the above embodiments, and will not be repeated here.

[0120] This application also provides a computer program product, including a computer program that, when executed by a processor, implements the steps of the wearable device tooling testing method described above.

[0121] The computer program product provided in this application addresses the technical problem of improving the accuracy of blood pressure measurement and assessment using wearable devices. Compared to the prior art, the beneficial effects of the computer program product provided in this application are the same as those of the wearable device tooling testing method provided in the above embodiments, and will not be repeated here.

[0122] The above description is only a part of the embodiments of this application and does not limit the patent scope of this application. All equivalent structural transformations made under the technical concept of this application and using the contents of the specification and drawings of this application, or direct / indirect applications in other related technical fields, are included in the patent protection scope of this application.

Claims

1. A method for testing tooling for wearable devices, characterized in that, The wearable device tooling testing method includes: Based on the preset theoretical blood pressure value, pulse signals and electrocardiogram signals are simultaneously transmitted to the preset wearable device; When the rising edge of the ECG signal is detected, a heart sound signal is transmitted to the wearable device according to the theoretical blood pressure value. The rising edge triggering refers to the voltage value of the ECG signal rising from below a preset rising edge triggering threshold to above the rising edge triggering threshold. The wearable device obtains the measured blood pressure value determined based on the received pulse signal, electrocardiogram signal, and heart sound signal; The measurement score of the wearable device is determined based on the theoretical blood pressure value and the measured blood pressure value.

2. The wearable device tooling testing method as described in claim 1, characterized in that, The step of transmitting a heart sound signal to the wearable device based on the theoretical blood pressure value when the rising edge of the electrocardiogram signal is detected includes: When the rising edge of the ECG signal is detected, a heart sound waveform is emitted by a heart sound signal generator, wherein the heart sound waveform is determined based on the theoretical blood pressure value; The heart sound waveform is converted into a heart sound signal using a passive speaker, and the heart sound signal is transmitted to the wearable device.

3. The wearable device tooling testing method as described in claim 2, characterized in that, The step of transmitting heart sound waveforms via a heart sound signal generator includes: Determine the average delay time between the electrocardiogram signal generator and the heart sound signal generator; The heart sound waveform pre-stored in the heart sound signal generator is shifted forward by the average delay time; The heart sound signal generator transmits the forward-shifted heart sound waveform.

4. The wearable device tooling testing method as described in claim 1, characterized in that, The step of simultaneously transmitting pulse signals and electrocardiogram signals to a preset wearable device based on a preset theoretical blood pressure value includes: Based on the theoretical blood pressure value, determine the theoretical pulse wave conduction time; Based on the theoretical pulse wave conduction time, the waveforms of the pulse signal and the electrocardiogram signal are adjusted so that the theoretical pulse wave conduction time and the waveform interval are equal, wherein the waveform interval is the time interval between the trough of the pulse signal and the peak of the R wave of the electrocardiogram signal. The adjusted pulse signal and the adjusted electrocardiogram signal are simultaneously transmitted to the wearable device.

5. The wearable device tooling testing method as described in claim 1, characterized in that, Before the step of synchronously transmitting pulse signals and electrocardiogram signals to a preset wearable device based on a preset theoretical blood pressure value, the method further includes: The software interface is displayed, which includes a blood pressure input box, an OK button, and a signal transmission button. In response to configuration actions performed on the blood pressure input field, determine the theoretical blood pressure value; In response to the trigger operation of the OK button, the ECG signal, pulse signal and heart sound signal are determined according to the theoretical blood pressure value, and the corresponding waveforms of the ECG signal, pulse signal and heart sound signal are displayed on the software interface; In response to a trigger operation on the signal transmission button, the steps of simultaneously transmitting pulse signals and electrocardiogram signals to a preset wearable device based on a preset theoretical blood pressure value, and subsequent steps, are performed.

6. The wearable device tooling testing method as described in claim 1, characterized in that, The step of determining the measurement score of the wearable device based on the theoretical blood pressure value and the measured blood pressure value includes: Calculate the absolute error between the theoretical blood pressure value and the measured blood pressure value; Based on the preset error range and scoring mapping relationship, the basic score corresponding to the absolute error value is determined; The variance of the fluctuation of multiple measured blood pressure values ​​output by the wearable device for the same theoretical blood pressure value within a preset time period is obtained. The measurement score is obtained by correcting the base score based on the variance of the fluctuation.

7. The wearable device tooling testing method as described in claim 1, characterized in that, Following the step of determining the measurement score of the wearable device, the method further includes: If the measured score is lower than a preset score threshold, obtain the actual timestamps of the ECG signal, heart sound signal and pulse signal received by the wearable device; Based on the actual timestamps, the relative delay between each sensor channel of the wearable device is calculated, wherein the sensor channels include an electrocardiogram detection channel, a heart sound acquisition channel, and a pulse detection channel; Identify abnormal delay channels whose relative delay exceeds the preset synchronization accuracy requirement, and compensate and correct the abnormal delay channels.

8. A tooling testing system, characterized in that, The tooling testing system includes a controller, a pulse-ECG synchronous signal source, and a heart sound simulation device. The pulse-ECG synchronous signal source includes a pulse signal generator and an ECG signal generator. The ECG signal generator and the heart sound simulation device are connected to a preset wearable device, and the pulse signal generator is in contact with the wearable device. The pulse-ECG synchronization signal source is used to control the pulse signal generator and the ECG signal generator to synchronously transmit pulse signals and ECG signals to the wearable device according to a preset theoretical blood pressure value. The heart sound simulation device is used to transmit a heart sound signal to the wearable device based on the theoretical blood pressure value when the rising edge of the electrocardiogram signal is detected. The wearable device is used to determine the measured blood pressure value based on the received pulse signal, electrocardiogram signal, and heart sound signal; The controller is used to determine the measurement score of the wearable device based on the theoretical blood pressure value and the measured blood pressure value.

9. The tooling testing system as described in claim 8, characterized in that, The heart sound simulation device includes a heart sound signal generator and a passive speaker. The heart sound signal generator is connected to the electrocardiogram signal generator, and the passive speaker is in contact with the wearable device. The heart sound signal generator is used to transmit a heart sound waveform when the rising edge of the electrocardiogram signal is detected, wherein the heart sound waveform is determined according to the theoretical blood pressure value; The passive speaker is used to convert the heart sound waveform into a heart sound signal and transmit the heart sound signal to the wearable device.

10. A storage medium, characterized in that, The storage medium is a computer-readable storage medium, and a computer program is stored on the storage medium. When the computer program is executed by a processor, it implements the steps of the wearable device tooling testing method as described in any one of claims 1 to 7.

Images