A radial artery hemostasis method and hemostat control system based on real-time pulse analysis

Abstract

The present application belongs to the technical field of radial artery compression hemostasis device, and particularly relates to a radial artery hemostasis method based on real-time pulse analysis and a hemostasis device control system. A slow and continuously changing force is applied to the radial artery puncture port by a pressure application module, while a pulse detection module transmits the forced feedback signal of the pulse at the puncture port to a master control module in real time. The master control module analyzes and processes the received feedback signal in real time and determines the current hemostasis state of the radial artery. Based on this, the pressure application module is controlled to adjust the pressure. The innovation of the present application lies in that the difference in the pulse feedback signal of the radial artery under different compression states is utilized, the relationship between the forced feedback signal of the pulse and the forced state of the radial artery is obtained through clinical trials, and the pressure is stabilized at a state where the radial artery blood flow is stable and the puncture port does not bleed. This scheme can overcome the individual differences between different patients and adaptively adjust the compression hemostasis force, thereby effectively reducing the incidence of radial artery occlusion and other related complications.

Description

Technical Field

[0001] This invention belongs to the technical field of radial artery compression hemostats, specifically relating to a radial artery hemostasis method and hemostat control system based on real-time pulse analysis. Background Technology

[0002] Cardiovascular disease, a major global public health challenge, causes more than 18 million deaths annually, accounting for approximately 32% of all deaths worldwide. With the accelerating aging of the population and lifestyle changes such as sedentary lifestyles and high-fat diets, the incidence of coronary atherosclerotic heart disease continues to rise. According to the "China Cardiovascular Health and Disease Report," the number of patients undergoing coronary intervention in my country has exceeded 1 million annually, and this number continues to grow at an average annual rate of 12%-15%. The radial artery approach, due to its advantages of rapid postoperative recovery and fewer complications, has become the preferred approach for more than 90% of coronary intervention procedures. However, effective hemostasis at the radial artery puncture site after surgery faces significant technical challenges. Traditional compression methods typically require continuous pressure for 4-6 hours, during which time it is crucial to ensure complete closure of the puncture site while maintaining distal blood circulation, placing extremely high demands on the precision of pressure control. Clinical studies have shown that maintaining this delicate balance is directly related to the incidence of postoperative complications, especially radial artery occlusion (RAO), a serious complication with an incidence of 5%-10%, which will permanently affect the patient's limb function.

[0003] In the early stages of radial artery hemostasis techniques, the elastic bandage spiral compression method was commonly used in clinical practice. While this method was inexpensive, it had significant operational limitations: First, the bandaging process required strict adherence to the "three-point pressure" principle, necessitating training of over 50 cases to master the correct technique; second, the stress relaxation characteristics of elastic materials resulted in a pressure attenuation rate of 15%-20% per hour, necessitating frequent adjustments (usually re-bandaging every 30 minutes); more importantly, non-selective compression often led to simultaneous compression of accompanying veins, resulting in limb swelling in approximately 28%-35% of cases. These shortcomings severely impacted patients' postoperative recovery experience and increased the workload of nursing staff.

[0004] To address the shortcomings of traditional hemostasis methods, second-generation hemostasis devices employ a modular pressurization design, primarily divided into two categories: mechanical pressure plate devices and pneumatic balloon devices. The pressure plate device controls the downward pressure of the polycarbonate pressure plate via an adjustable knob, achieving a pressure adjustment accuracy of ±5 mmHg. The pneumatic balloon device uses a miniature air pump to achieve linear pressure control from 5-50 mmHg. Clinical comparative trials show that these devices shorten hemostasis time to 2-3 hours and reduce venous compression rate to 18%-25%. However, in-depth research reveals systemic defects in existing devices: firstly, pressure calibration lacks a unified standard, with actual contact pressure differences of 30%-40% between different brands of devices at the same nominal pressure; secondly, a dynamic adjustment mechanism is lacking, failing to compensate in real-time for fluctuations in patient blood pressure (especially systolic blood pressure changes of ±20 mmHg); and thirdly, a lack of a visual feedback system means that 75% of clinical operations rely solely on the operator's experience, resulting in an inappropriate pressure usage rate remaining between 12%-18%.

[0005] Previous studies have shared a common approach: they typically determine the safety of a given pressure level by consulting patients about their experience and doctors' expertise, thereby quantifying a standardized pressure range for application to every patient. However, the industry currently lacks relatively scientific evaluation standards to support the safety of this pressure range. It is well known that differences in skin thickness, body size, and radial artery elasticity among individuals can make it difficult to apply a pressure range measured in one patient to others. Furthermore, simply quantifying the pressure between the pressure plate or balloon and the skin does not directly reflect the compression effect on the radial artery puncture site.

[0006] Therefore, breakthroughs are urgently needed in developing radial artery hemostasis methods that can adapt to individual physiological differences. Summary of the Invention

[0007] To address the problems mentioned in the background section, a radial artery hemostasis method and hemostasis control system based on real-time pulse analysis are proposed.

[0008] One of the objectives of this invention is to provide a radial artery hemostasis method based on real-time pulse analysis. This method can accurately determine the state of compression at the radial artery puncture site, making it easier for the control system to control the compression hemostasis force within an ideal range, so that the radial artery puncture site is in a state that can both successfully stop bleeding and maintain unobstructed blood flow in the blood vessel for a long time.

[0009] Specifically, based on the differences in radial artery pulsation under different compression conditions, a slowly varying and continuous force is applied to the radial artery puncture site, specifically divided into a pressurization process and a decompression process. During the process, the radial artery compression feedback signal is continuously detected. At the same time, combined with blood flow detection equipment, the radial artery compression feedback signal is analyzed to derive a hemostasis critical state determination model, and this model is applied to determine the optimal compression effect of the radial artery compression hemostat.

[0010] The pressurization process involves continuously applying a slowly increasing force to the radial artery puncture site. As the pressure increases, the radial artery is gradually compressed, and blood flow is gradually obstructed. The radial artery compression feedback signal detected by the sensor will first increase and then decrease until it disappears completely. At this point, the radial artery is completely blocked, and blood flow stops.

[0011] The decompression process involves continuously and slowly reducing the pressure applied to the radial artery puncture site. As the applied pressure decreases, the radial artery blood flow gradually recovers, and the radial artery forced feedback signal detected by the sensor will first increase and then decrease until it disappears completely. At this point, there is no interaction between the corresponding sensor and the radial artery puncture site.

[0012] The critical state mentioned in the hemostasis critical state determination model is the state in which the radial artery puncture site can achieve successful hemostasis while maintaining unobstructed blood flow within the blood vessel. The determination model is calculated by comprehensively analyzing blood flow detection and radial artery forced feedback signals. That is, it analyzes the characteristics of the radial artery forced feedback signal corresponding to the critical state, derives the corresponding model, and applies this model to the radial artery compression hemostat control system to determine the optimal compression effect of the radial artery compression hemostat.

[0013] The second objective of this invention is to provide a radial artery compression hemostat control system based on real-time pulse analysis, characterized in that it includes: a main control module, an interaction module, a pressure application module, and a pulse detection module; its system control modes are divided into calibration mode and stable mode.

[0014] The control system includes the following modules (such as...) Figure 1 As shown):

[0015] Main control module: Composed of a microprocessor (MCU) and its supporting circuits, it has a built-in dynamic pulse signal analysis algorithm and pressure control logic; it receives and processes the raw signals from the pulse detection module in real time, extracts the pulse response amplitude and frequency characteristics through fast analog-to-digital conversion (ADC), and generates pressure regulation commands based on a preset hemostasis critical state judgment model and sends them to the pressure application module.

[0016] Interactive module: Includes physical buttons, color LED indicators, speaker, and electronic screen, via SPI, I... 2Communication protocols such as C communicate with the main control module to achieve a closed loop of human-computer interaction.

[0017] The pressure application module comprises a small airbag, a miniature air pump, a solenoid valve, and corresponding connecting tubing. The airbag is secured above the radial artery puncture site via a hemostat wristband. The air pump's inflation speed is precisely controlled by a PWM signal from the main control module, and the solenoid valve's depressurization speed is precisely controlled by the main control module via a drive circuit. The pressure application module is electrically connected to the main control module via wires to transmit control signals.

[0018] The pulse detection module consists of a flexible piezoelectric thin-film sensor and a signal acquisition circuit. The flexible piezoelectric thin-film sensor converts the force signal from the radial artery's forced feedback into an electrical signal. The signal acquisition circuit performs impedance matching, filtering, and amplification on the sensor's output electrical signal, ultimately converting the weak radial artery forced feedback signal into a signal that can be acquired by the main control module's ADC. The pulse detection module is electrically connected to the main control module via wires for signal transmission.

[0019] The calibration mode is an operation process for analyzing the user's optimal hemostatic pressure range, including: the main control module controls the pressure application module to continuously and slowly change the pressure; the pulse detection module continuously detects changes in the radial artery forced feedback signal and feeds the signal back to the main control module; the main control module analyzes and calculates to determine the user's optimal hemostatic pressure range at this time.

[0020] The stable mode is the operational process for achieving the optimal hemostatic pressure range determined by the calibration mode. This includes: the main control module controlling the pressure application module to stabilize the pressure within the optimal hemostatic pressure range; the pulse detection module continuously detecting changes in the radial artery forced feedback signal and feeding the signal back to the main control module; the main control module monitoring the pressure feedback for abnormalities in real time, maintaining the pressure if no abnormalities are found, and re-executing the calibration mode if abnormalities persist and certain conditions are met.

[0021] This invention integrates a critical hemostasis state determination model by continuously detecting and analyzing radial artery pulses under different pressure conditions. It can accurately identify the current compression state at the radial artery puncture site, avoiding the use of a specific pressure range to measure the compression hemostasis of all patients.

[0022] This invention discloses a radial artery hemostasis method and hemostatic device control system based on real-time pulse analysis, which can overcome the influence of differences in age, gender, body size, skin thickness, and vascular elasticity among different patients. For different patients, adaptive analysis calculates the optimal compression hemostasis pressure range and precisely stabilizes the applied pressure within this range. Personalized treatment can tailor precise compression hemostasis methods based on the patient's physiological indicators and environmental factors, significantly improving the effectiveness of compression hemostasis and effectively reducing the risk of postoperative complications. Through intelligent sensing and analysis technology, treatment transitions from "standardization" to "personalization" and "precision." Attached Figure Description

[0023] The present invention will be further described with reference to the accompanying drawings, but the embodiments in the drawings do not constitute any limitation on the present invention. For those skilled in the art, other drawings can be obtained based on the following drawings without creative effort.

[0024] Figure 1 This is a schematic diagram of the module connections of the control system of the present invention;

[0025] Figure 2 A flowchart of the control system process;

[0026] Figure 3 for Figure 2 An example of the calibration mode;

[0027] Figure 4 for Figure 2 An example of a stable mode; Detailed Implementation

[0028] To more clearly illustrate the technical details of the present invention, the embodiments of the present invention will be further described in detail below with reference to the accompanying drawings.

[0029] This embodiment specifically includes a radial artery hemostasis method and a hemostatic device control system based on real-time pulse analysis. The radial artery hemostasis method based on real-time pulse analysis can accurately determine the compression state of the radial artery puncture site, facilitating the control of the compression force within an ideal range, ensuring that the radial artery puncture site remains in a state that achieves successful hemostasis while maintaining unobstructed blood flow within the vessel for an extended period.

[0030] Based on the differences in radial artery pulsation under different compression conditions, a slowly varying and continuous force is applied to the radial artery puncture site, specifically divided into a pressurization process and a decompression process. During the process, the radial artery compression feedback signal is continuously detected. At the same time, combined with blood flow detection equipment, the radial artery compression feedback signal is analyzed and calculated to derive a hemostasis critical state determination model. This model is then applied to the radial artery compression hemostat control system to determine the optimal compression effect of the radial artery compression hemostat.

[0031] The pressurization process involves applying a slowly increasing and continuous force to the radial artery puncture site. As the applied force increases, the radial artery is gradually compressed, and blood flow is gradually obstructed. The radial artery compression feedback signal detected by the sensor will first increase and then decrease until it disappears completely. At this point, the radial artery is completely blocked, and blood flow stops.

[0032] The decompression process involves gradually and continuously reducing the pressure applied to the radial artery puncture site. As the applied pressure decreases, the radial artery blood flow gradually recovers, and the radial artery forced feedback signal detected by the sensor will first increase and then decrease until it disappears completely. At this point, there is no interaction between the corresponding sensor and the radial artery puncture site.

[0033] The critical state mentioned in the hemostasis critical state determination model is the state in which the radial artery puncture site can achieve successful hemostasis while maintaining unobstructed blood flow within the blood vessel. The determination model is calculated by comprehensively analyzing blood flow detection and radial artery forced feedback signals, that is, analyzing the characteristics of the radial artery forced feedback signals when the critical state is reached, and deriving the corresponding model.

[0034] Furthermore, during the pressurization process, the intensity of the radial artery forced feedback signal first increases and then decreases, reaching a maximum value. Similarly, during the depressurization process, the intensity of the radial artery forced feedback signal also first increases and then decreases, reaching a maximum value. The depressurization process can be considered the reverse of the pressurization process. Therefore, it is necessary to record the maximum value P of the radial artery forced feedback signal intensity during the above processes. MAX .

[0035] During the decompression process, a blood flow detection device is used to monitor the blood flow in the compressed radial artery. The radial artery will gradually restore blood flow from a state of complete forced occlusion. When the blood flow detection device detects blood flow, the current radial artery forced feedback signal intensity P1 and the corresponding pressure value F1 need to be recorded. These two values ​​will be used to determine the optimal pressure range.

[0036] After continuous decompression, the applied pressure was insufficient to achieve hemostasis, and bleeding began to occur at the puncture site. At this point, it is necessary to record the current radial artery compressive feedback signal intensity P. MIN Corresponding pressure value FMIN .

[0037] Since the intensity P of the radial artery forced feedback signal first increases and then decreases during both the pressurization and depressurization processes, therefore, except for P... MAX In addition, with P1 and P MIN Values ​​of the same intensity will appear twice, each corresponding to a different pressure F.

[0038] When the intensity P of the radial artery forced feedback signal is between P1 and P2 MIN When it is between, it is considered to be in the corresponding pressure range (F) MIN (F1) The radial artery is in a good state of hemostasis.

[0039] Because of differences in age, gender, body size, skin thickness, and vascular elasticity among patients, the measured P values ​​vary from patient to patient. MAX P1 and P MIN There are differences, but P MAX P1 and P MIN The relative proportions between them are basically fixed and do not change significantly with differences among patients. Furthermore, Defined as coefficient m, Defined as the coefficient n.

[0040] Here, the following variable is defined: the maximum value of the radial artery compressive feedback signal intensity measured in a patient during the above-mentioned compression process is p. max The intensity of the radial artery forced feedback signal during the aforementioned decompression process in this patient was p. t When p t First equals m*p max At this point, it is assumed that blood begins to flow in the radial artery under the current pressure f1; when p equals n*p for the second time... max Then it is considered that under the current pressure f min The radial artery puncture site was in a critical state of impending bleeding, therefore, when f was in the interval (f... min When f1), the radial artery is in a good state of hemostasis.

[0041] Furthermore, in actual implementation, sufficient safety margin should be reserved, the range of f should be further narrowed, and it should be kept as far away from f as possible. min Therefore, during the decompression process, when p t First equals m*p max The pressure reduction continues, at which point p t It will gradually increase and approach p max As the pressure continues to decrease, at p t =p max Afterwards, pt will gradually decrease, when p t The second time equals m*pmax When the corresponding pressure is f0, and f is in the interval (f0, f1), the radial artery is in the optimal state of hemostasis. At this time, it is only necessary to control the pressure to ensure p. max >p t >m*p max The conditions will be met.

[0042] This embodiment also includes a radial artery compression hemostat control system and its control modes based on real-time pulse analysis. The system consists of a main control module, an interaction module, a pressure application module, and a pulse detection module; its system control modes are divided into a calibration mode and a stable mode.

[0043] like Figure 1 As shown: The main control module consists of a microprocessor (MCU) and its supporting circuitry. It incorporates a dynamic radial artery forced feedback signal analysis algorithm and pressure control logic. It receives and processes raw signals from the pulse detection module in real time, extracts pulse response amplitude and frequency characteristics through rapid analog-to-digital conversion (ADC), and generates pressure regulation commands based on a preset hemostasis critical state judgment model, sending them to the pressure application module. The interaction module includes physical buttons, color LED indicators, a speaker, and an electronic screen. It communicates with the main control module via SPI, I2C, and other communication protocols to achieve a closed-loop human-machine interaction. Specifically:

[0044] Buttons: Supports input of start / stop and calibration mode switching commands;

[0045] Indicator lights: Real-time display of system status (blue: running, yellow: calibration mode, green: stable mode);

[0046] Speaker: Announces operation prompts (such as "Calibration in progress, please remain still" or "Stable mode has been entered");

[0047] Electronic screen: dynamically displays pressure curves, pulse waveforms, and hemostasis timing;

[0048] The pressure application module includes a small airbag, a miniature air pump, a solenoid valve, and corresponding connecting pipes. The airbag is fixed directly above the radial artery puncture site via a hemostat wristband. The air pump's inflation speed is precisely controlled by a PWM signal from the main control module. The solenoid valve's depressurization speed is precisely controlled by the main control module via a drive circuit. The pressure application module is electrically connected to the main control module via wires to transmit control signals. The pulse detection module consists of a flexible piezoelectric thin-film sensor and a signal acquisition circuit. The flexible piezoelectric thin-film sensor has excellent sensitivity and good biocompatibility, and can respond sensitively to weak radial artery compressive feedback signals. The signal acquisition circuit performs impedance matching and filtering on the sensor signal, ultimately converting the weak radial artery compressive feedback signal into a signal that can be acquired by the main control module's ADC. The pulse detection module is electrically connected to the main control module via wires to transmit signals.

[0049] Control system workflow as follows Figure 2 As shown, the specific process is as follows:

[0050] S1. Press and hold the "ON / OFF" button to turn on the device, and press the "ON / OFF" button briefly to enter calibration mode;

[0051] S2. Automatically enters stable mode after calibration mode is completed;

[0052] S3. If a persistent abnormal pressure feedback is detected while executing stable mode, re-enter calibration mode;

[0053] S4. After the stable mode has been maintained for a certain period of time, the attending physician shall determine whether to terminate the operation and press and hold the "ON / OFF" button to turn off the machine and release pressure.

[0054] The specific implementation steps of the calibration mode are as follows: Figure 3 As shown:

[0055] After powering on, briefly press the "ON / OFF" button. The system will then announce through the speaker, "Calibration in progress, please remain still," indicating that it has entered calibration mode and the indicator light will turn yellow.

[0056] Under the control of the main control module, the air pump in the pressure module begins to slowly inflate the air. At the same time, the pulse detection module begins to continuously collect radial artery forced feedback signals and feeds the collected radial artery forced feedback signals back to the main control module for analysis and processing in real time.

[0057] The ADC section within the main control module performs analog-to-digital conversion on the radial artery forced feedback signal output from the pulse detection module, and records the peak intensity p in a single pulse cycle of the current feedback signal. t1 And continuously update p t1 The maximum value. As the air pump continues to inflate, the pressure at the radial artery puncture site gradually increases, p t1It shows a trend of first increasing and then decreasing, which will lead to p t1 Once the maximum value is reached, updates will cease, and the main control module will... t1 The maximum value p M Save it.

[0058] At this time, if the maximum peak intensity p recorded by the main control module M If no update is performed for more than 10 consecutive pulse cycles, the calibration mode will proceed to the next stage:

[0059] The main control module stops the air pump in the pressure application module from inflating and controls the solenoid valve to slowly deflate and reduce pressure. As the pressure decreases, the intensity of the radial artery compression feedback signal detected by the pulse detection module gradually increases. At this time, the main control module records the peak intensity p of each pulse cycle again. t2 and compare it with p1 = m * p M When p is compared, t2 When p1 is ≥, the radial artery is in the optimal state of compression and hemostasis. At this time, the main control module controls the solenoid valve of the pressure application module to stop releasing air and reducing pressure, and the system enters the stable mode.

[0060] like Figure 4 As shown, when the system enters stable mode, the speaker in the interactive module will prompt "Entering pressure stabilization mode," and the indicator light will turn green, while the hemostasis timer on the electronic screen will start. Even when the system is in stable mode, the pulse detection module will continue to detect the radial artery compression feedback signal and feed the detected signal back to the main control module in real time.

[0061] When the detected radial artery forced feedback signal intensity p t3 Satisfying m*p M -p t3 >m*p M When the pressure drops to 10%, an abnormal pressure is considered to have occurred. The main control module controls the pressure application module to take corresponding pressure increase and decrease measures and records the number of abnormal occurrences. If the number of abnormal occurrences reaches 5 within 5 minutes, the data obtained from the previous calibration mode is considered invalid, and the system re-enters the calibration mode.

[0062] Before entering calibration mode from the failed stable mode, the main control module controls the solenoid valve of the pressure application module to slowly release and depressurize. The intensity p4 of the radial artery forced feedback signal detected by the pulse detection module may gradually decrease, or it may increase first and then decrease. When the value of p4 decreases to m*p M When the target reaches 120%, the system re-enters calibration mode and repeats the above steps until the goal of radial artery hemostasis is effectively achieved.

[0063] It will be apparent to those skilled in the art that the present invention is not limited to the details of the exemplary embodiments described above, and that the invention can be implemented in other specific forms without departing from its spirit or essential characteristics. Therefore, the embodiments should be considered in all respects as exemplary and non-limiting, and the scope of the invention is defined by the appended claims rather than the foregoing description. Thus, all variations falling within the meaning and scope of equivalents of the claims are intended to be included within the present invention. No reference numerals in the claims should be construed as limiting the scope of the claims.

[0064] Furthermore, it should be understood that although this specification describes embodiments, not every embodiment contains only one independent technical method. This narrative style is merely for clarity. Those skilled in the art should consider the specification as a whole, and the technical methods in each embodiment can also be appropriately combined to form other embodiments that can be understood by those skilled in the art.

Claims

1. A radial artery compression hemostat control system based on real-time pulse analysis, characterized in that, include: Main control module, interaction module, pressure application module, pulse detection module; The system control modes are divided into calibration mode and stable mode. The calibration mode determines the optimal hemostatic pressure range for the current patient through a pulse feedback signal characteristic coefficient calibration mechanism, while the stable mode maintains pressure stability through a dual-threshold abnormality judgment mechanism. The calibration mode includes the following steps: the main control module controls the pressure application module to slowly inflate and pressurize, the pulse detection module continuously collects the radial artery forced feedback signal, records the peak intensity pt1 within a single pulse cycle, and continuously updates the maximum value of pt1; once pt1 reaches its maximum value, it will no longer be updated, and the main control module saves the maximum value pM of pt1. If the maximum peak intensity pM recorded by the main control module is not updated for more than 10 consecutive pulse cycles, the main control module controls the pressure application module to slowly release air and reduce pressure. During the decompression process, the blood flow detection device is used to monitor the blood flow of the currently compressed radial artery. The radial artery will gradually restore blood flow from a state of complete forced occlusion. When the blood flow detection device detects blood flow, it needs to record the current radial artery forced feedback signal intensity p1. The intensity of the radial artery forced feedback signal detected by the pulse detection module will gradually increase. The main control module records the peak intensity pt2 in each pulse cycle again and compares it with p1. When pt2≥p1, the radial artery is in the optimal state of compression hemostasis. At this time, the main control module controls the solenoid valve of the pressure application module to stop releasing air and reducing pressure, and the system enters the stable mode. When the system is in stable mode, the pulse detection module will continue to detect the radial artery forced feedback signal and feed the detected signal back to the main control module in real time. When the detected radial artery forced feedback signal intensity pt3 satisfies p1-pt3>p1*10%, it is considered that there is a pressure abnormality. The main control module controls the pressure application module to take corresponding pressure increase and decrease measures and records the number of abnormal occurrences. If the number of abnormal occurrences reaches 5 within 5 minutes, the data obtained from the previous calibration mode is considered invalid, and the system re-enters the calibration mode.

2. The control system according to claim 1, characterized in that, The interactive module consists of buttons, indicator lights, a speaker, and an electronic screen: the buttons are used for start / stop and mode switching commands; the indicator lights display the system status, with yellow for calibration mode and green for stable mode; the speaker broadcasts operation prompts; and the electronic screen dynamically displays the pressure curve, pulse waveform, and hemostasis timing.

3. The control system according to claim 1, characterized in that, The pressure application module includes a small airbag, a miniature air pump, a solenoid valve, and connecting pipes. The airbag is fixed above the radial artery puncture site by a hemostat wristband. The main control module controls the air pump inflation speed through a PWM signal and controls the solenoid valve depressurization speed through a drive circuit, so as to achieve continuous pressure adjustment with an adjustment accuracy of ±5mmHg.

4. The control system according to claim 1, characterized in that, The pulse detection module consists of a flexible piezoelectric thin-film sensor and a signal acquisition circuit; the flexible piezoelectric thin-film sensor is responsible for converting the force signal fed back by the radial artery into an electrical signal; the signal acquisition circuit performs impedance matching, filtering and amplification processing on the signal.

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