Radial artery hemostasis compressor

Abstract

The application discloses a radial artery hemostasis compressor and relates to the technical field of hemostasis compressors.The radial artery hemostasis compressor comprises an upper end cover and a shell, a wrist strap and a gas bag assembly are arranged at the bottom of the shell, a circuit board and a battery are arranged in the shell, a control button and a display screen are arranged on the circuit board, a gas pump and a pressure relief valve are arranged in the shell, the gas pump and the pressure relief valve are connected with a quick plug connector through a third pipeline and a first pipeline respectively, and the quick plug connector is connected with the gas bag assembly through a second pipeline.The radial artery hemostasis compressor provided by the application sets different hemostasis compression pressure thresholds for different groups of people, thereby realizing accurate adjustment of the pressure of hemostasis compression, has high practicability, meets the actual needs of the radial artery hemostasis compressor, is provided with the gas bag assembly, realizes the change from traditional overall compression to bleeding point targeted compression, reduces unnecessary compression of non-bleeding areas, realizes a staged pressure relief strategy of first periphery and then center, and guarantees hemostasis and restores distal blood flow as soon as possible.

Description

Technical Field

[0001] This invention relates to the field of hemostatic compression device technology, specifically a radial artery hemostatic compression device. Background Technology

[0002] Transradial artery intervention (TRI) is a common method for the diagnosis and treatment of cardiovascular diseases. Post-procedure, effective compression of the radial artery puncture site is necessary for hemostasis. Traditional hemostatic devices often employ a fixed single-balloon or multi-balloon structure. Existing radial artery hemostatic devices have the following drawbacks:

[0003] 1. Precise pressure adjustment is difficult. Different patients have varying physiological conditions such as radial artery diameter, vessel wall thickness, and blood pressure, resulting in different appropriate pressures for hemostasis. Current pneumatic compression devices struggle to achieve precise pressure control, easily leading to excessive or insufficient pressure. Excessive pressure may cause over-compression of the vessel, affecting distal blood supply and causing tissue ischemia and necrosis; insufficient pressure will fail to effectively stop bleeding, leading to oozing at the puncture site and hematoma formation.

[0004] 2. It lacks a digital display function, so it cannot directly reflect the pressure level and cannot adjust the pressure level as needed.

[0005] 3. Currently, the existing hemostatic compression device uses an integrated structure. In actual use, the location of the bleeding point is determined by medical staff through visual identification. Then, the hemostatic compression device is placed at the bleeding point of the radial artery. The integrated structure of the airbag applies pressure to the entire airbag contact surface for hemostasis, but it cannot provide targeted hemostasis and compression at the bleeding point.

[0006] 4. The hemostatic compression device uses an integrated structure for the cuff. Prolonged compression may lead to excessive pressure on the blood vessels, affecting distal blood supply. Conversely, insufficient compression may result in ineffective hemostasis, causing oozing at the puncture site. For patients with complex conditions and other complications, a device is needed where the cuff can compress the bleeding point for a period of time, then the outer ring of compression around the bleeding point can be released before releasing the compression at the bleeding point itself. This ensures effective hemostasis while preventing excessive pressure on the patient's blood vessels. Summary of the Invention

[0007] The purpose of this invention is to address the above-mentioned problems by providing a radial artery hemostatic compressor. This device includes a circuit board, control buttons, and a display screen. It allows for the setting of different hemostatic pressure thresholds for different individuals, enabling precise adjustment of the hemostatic pressure. It is highly practical, meeting the actual needs of radial artery hemostatic compressors. The display screen reflects the pressure level, while the buttons control the pressure adjustment, greatly improving the device's information feedback and operational performance. It addresses the practical needs of different individuals for adjusting the pressure of the hemostatic compressor. The device also includes an airbag assembly, transforming traditional overall compression into targeted compression at the bleeding point, reducing unnecessary compression in non-bleeding areas. This allows for a phased pressure relief strategy, from the periphery to the center, ensuring hemostasis while restoring distal blood flow as quickly as possible.

[0008] To achieve the above objectives, the technical solution adopted by the present invention is as follows:

[0009] A radial artery hemostatic compressor includes an upper cap and a housing. A wristband and an airbag assembly are provided at the bottom of the housing. A circuit board and a battery are provided inside the housing. Control buttons and a display screen are provided on the circuit board. An air pump and a pressure relief valve are provided inside the housing. The air pump and the pressure relief valve are connected to a quick-connect connector through a third pipe and a first pipe, respectively. The quick-connect connector is connected to the airbag assembly through a second pipe.

[0010] As a further improvement to the above solution, a protective film with a transparent sheet structure is provided on the upper surface of the upper cover.

[0011] As a further improvement to the above solution, a pressure sensor is installed on the first pipeline.

[0012] As a further improvement to the above solution, the lower part of the wristband is bonded together with Velcro.

[0013] As a further improvement to the above solution, a limiting seat is provided outside the air pump and the pressure relief valve and inside the housing.

[0014] As a further improvement to the above solution, the first pipe is provided with an L-shaped parallel plate-like limiting plate on its exterior.

[0015] As a further improvement to the above solution, the airbag assembly includes a support member and a split airbag, the split airbag being installed in the wristband via the support member.

[0016] As a further improvement to the above solution, the split airbag is a polygonal bladder structure made of transparent material. Multiple split airbags are combined in a honeycomb structure, and each split airbag can be independently inflated and deflated.

[0017] As a further improvement to the above solution, a color sensor, an exhaust valve, and a fourth pipe are provided inside the split-type airbag. A one-way valve is provided at the end of the fourth pipe that extends out of the split-type airbag. A fifth pipe on the one-way valve is connected to a multi-pipe connector, and the multi-pipe connector is connected to a second pipe.

[0018] As a further improvement to the above solution, a light strip is provided on the outside of the color sensor, and multiple LED light sources are arranged around the light strip.

[0019] Compared with the prior art, the beneficial effects of the present invention are as follows: It is equipped with a circuit board, control buttons, and a display screen, allowing for the setting of different hemostatic compression pressure thresholds for different populations as needed, thereby achieving precise adjustment of the hemostatic compression pressure. It is highly practical, meeting the actual needs of radial artery hemostatic compressors. The display screen reflects the pressure level, while the buttons control the pressure of the hemostatic compressor, greatly improving the device's information feedback function and operational performance, addressing the actual needs of different populations for adjusting the pressure of the hemostatic compressor. The inclusion of an airbag assembly transforms traditional overall compression into targeted compression at the bleeding point, reducing unnecessary compression in non-bleeding areas and enabling a phased pressure relief strategy from the periphery to the center, ensuring hemostasis while restoring distal blood flow as early as possible. Attached Figure Description

[0020] Figure 1 This is a three-dimensional structural diagram of the present invention.

[0021] Figure 2 This is an exploded view of the invention.

[0022] Figure 3 This is a three-dimensional structural diagram of the control button location of the present invention.

[0023] Figure 4 This is a three-dimensional structural diagram of the air pump location of the present invention.

[0024] Figure 5 This is a side view of the airbag assembly of the present invention.

[0025] Figure 6 This is a schematic diagram of the three-dimensional structure of the split-type airbag of the present invention.

[0026] Figure 7 This is a three-dimensional schematic diagram of the internal structure of the split-type airbag of the present invention.

[0027] Figure 8 This is a schematic diagram of the main structure of the split-type airbag of the present invention.

[0028] Figure 9 This is a system diagram of the core architecture of the control circuit of the present invention.

[0029] The text labels in the diagram represent: 1. Protective film; 2. Top cover; 3. Display screen; 4. Control buttons; 5. Circuit board; 6. Battery; 7. Housing; 8. Airbag assembly; 9. Wristband; 10. First pipe; 11. Pressure sensor; 12. Quick connector; 13. Second pipe; 14. Third pipe; 15. Air pump; 16. Pressure relief valve; 17. Multi-pipe connector; 801. Support component; 802. Split airbag; 803. Fourth pipe; 804. Color sensor; 805. Exhaust valve; 806. Light strip; 807. LED light source; 808. One-way valve; 809. Fifth pipe. Detailed Implementation

[0030] To enable those skilled in the art to better understand the technical solution, the present invention will be described in detail below with reference to embodiments. The description in this part is only exemplary and explanatory, and should not be used to limit the scope of protection of the present invention in any way.

[0031] Example 1:

[0032] like Figures 1-8 As shown, the specific solution of this embodiment is as follows: a radial artery hemostatic compressor, including an upper end cover 2 and a housing 7. A wristband 9 and an airbag assembly 8 are provided at the bottom of the housing 7. A circuit board 5 and a battery 6 are provided inside the housing 7. A control button 4 and a display screen 3 are provided on the circuit board 5. An air pump 15 and a pressure relief valve 16 are provided inside the housing 7. The air pump 15 and the pressure relief valve 16 are connected to a quick-connect connector 12 through a third pipe 14 and a first pipe 10, respectively. The quick-connect connector 12 is connected to the airbag assembly 8 through a second pipe 13.

[0033] More specifically, circuit board 5 is electrically connected to various components such as control button 4, display screen 3, air pump 15, battery 6, pressure relief valve 16, pressure sensor 11, color sensor 804, and exhaust valve 805. Circuit board 5 includes an MCU chip, ARM CortexM0, with a main frequency of 32MHz; it integrates 12-bit ADC, PWM, I²C, and UART. Pressure sensor 11 performs pressure detection on the first pipeline 10 and sends a signal to circuit board 5. Circuit board 5 performs logical analysis, processing, and judgment on the received signal. Display screen 3 displays the specific pressure value. The pressure can be adjusted by controlling button 4. When control button 4 is pressed, circuit board 5 performs logical analysis, processing, and judgment on the received signal, sends a control signal to pressure relief valve 16, and causes pressure relief valve 16 to perform pressure relief operation, thereby realizing precise pressure adjustment and digital display control.

[0034] As a preferred embodiment of the above, a protective film 1 with a transparent sheet structure is provided on the upper surface of the upper cover 2.

[0035] More specifically, the protective film 1 is made of high-transparency PC or PET with a thickness of 0.2–0.4 mm, which serves to prevent dust and scratches.

[0036] As a preferred embodiment of the above, a pressure sensor 11 is provided on the first pipe 10.

[0037] More specifically, the pressure sensor 11 is used to sense the pressure inside the first pipe 10, with a range of 0-400 mmHg and an accuracy of ±1 mmHg, and is used for closed-loop feedback.

[0038] As a preferred embodiment of the above, the lower part of the wristband 9 is bonded together with Velcro.

[0039] More specifically, the lower part of the wristband 9 is attached by Velcro, with the hook side at the end of the wristband 9 and the loop side at the other end of the wristband 9, and the adhesive length is ≥3cm.

[0040] As a preferred embodiment of the above, a limiting seat is provided outside the air pump 15 and the pressure relief valve 16 and inside the housing 7.

[0041] More specifically, the limit seat has a semi-enclosed structure and restricts the displacement of the air pump 15 and the pressure relief valve 16.

[0042] As a preferred embodiment of the above, the first pipe 10 is provided with a limiting plate with an L-shaped parallel plate structure on its exterior.

[0043] More specifically, the limiting plate restricts the displacement of the first pipe 10.

[0044] As a preferred embodiment of the above, the airbag assembly 8 includes a support member 801 and a split airbag 802, the split airbag 802 being installed in the wristband 9 via the support member 801.

[0045] More specifically, the support 801 is used to facilitate the placement of the split airbag 802 within the wristband 9.

[0046] As a preferred embodiment of the above, the split airbag 802 is a polygonal bladder-like structure made of transparent material. Multiple split airbags 802 are combined in a honeycomb structure, and each split airbag 802 can be independently inflated and deflated.

[0047] More specifically, the split-type airbag 802 uses a highly transparent medical-grade TPU film with a thickness of 0.1 mm and a visible light transmittance of ≥90%, which facilitates the color sensor 804 to identify blood penetration. Each airbag can be independently inflated and deflated to achieve targeted compression of bleeding points and reduce unnecessary compression of non-bleeding areas. Staff can also adjust it as needed.

[0048] As a preferred embodiment of the above, the split airbag 802 is provided with a color sensor 804, an exhaust valve 805 and a fourth pipe 803. The end of the fourth pipe 803 extending out of the split airbag 802 is provided with a one-way valve 808. The fifth pipe 809 on the one-way valve 808 is connected to a multi-pipe connector 17, and the multi-pipe connector 17 is connected to a second pipe 13.

[0049] More specifically, the one-way valve 808 uses a miniature solenoid valve to prevent backflow and ensure stable pressure in other airbags during staged depressurization. It is controlled by circuit board 5. The exhaust valve 805 is a miniature solenoid valve, such as the SMC S070 series (6mm wide, 10ms response, rated voltage 3V / 5V), driven by the MCU in circuit board 5 through a MOS transistor for rapid depressurization. The color sensor 804 is an RGB three-channel digital sensor that detects bleeding points by detecting color changes in blood seepage. When staged depressurization is required, in stage 1, only the exhaust valve 805 on the outer split airbag 802 is activated, while the middle split airbag 802 maintains a certain pressure to continue hemostasis. In stage 2, the exhaust valve 805 on the middle split airbag 802 is activated, gradually reducing the pressure to a safe level.

[0050] As a preferred embodiment of the above, a light strip 806 is provided outside the color sensor 804, and a plurality of LED light sources 807 are arranged around the light strip 806.

[0051] More specifically, multiple LED light sources 807 are arranged around the light strip 806 to provide stable white light supplement and eliminate ambient light interference.

[0052] The specific working principle of this invention is as follows:

[0053] Circuit board 5 is electrically connected to control buttons 4, display screen 3, air pump 15, battery 6, pressure relief valve 16, pressure sensor 11, color sensor 804, exhaust valve 805, and other components. Circuit board 5 includes an MCU chip, ARM CortexM0, with a main frequency of 32MHz; it integrates 12-bit ADC, PWM, I²C, and UART. Pressure sensor 11 performs pressure detection on the first pipeline 10 and sends a signal to circuit board 5. Circuit board 5 performs logical analysis, processing, and judgment on the received signal. Display screen 3 displays the specific pressure value. The pressure can be adjusted by control buttons 4. When control button 4 is pressed, circuit board 5 performs logical analysis, processing, and judgment on the received signal, sends a control signal to pressure relief valve 16, and causes pressure relief valve 16 to perform pressure relief operation, thereby achieving precise pressure adjustment and digital display control. Color sensor 804 identifies bleeding points by detecting color changes in blood seepage. Medical staff can set the target pressure (e.g., 180mmHg) by pressing buttons.

[0054] Air pump 15 starts, inflating the bleeding point airbag or adjacent airbags to the target value. Color sensor 804 is an RGB three-channel digital sensor that identifies the bleeding point by detecting the color change of blood seepage. When a staged depressurization operation is required, in stage 1, only the exhaust valve 805 on the outer ring split airbag 802 is activated, while the middle split airbag 802 maintains a certain pressure to continue hemostasis. In stage 2, the exhaust valve 805 on the middle split airbag 802 is activated, gradually reducing the pressure to a safe level. Staff can adjust the safety pressure according to the patient's actual situation and needs.

[0055] Example 2:

[0056] In a preferred embodiment, the control circuit used in the radial artery hemostatic compressor is described in detail based on Example 1:

[0057] The radial artery hemostatic compressor control circuit disclosed in this embodiment aims to achieve precise compression control of the radial artery puncture site, targeted identification of bleeding points, and staged pressure relief adjustment. The control circuit works in conjunction with the mechanical structure of the hemostatic compressor (such as the housing 7, the air bladder assembly 8, the air pump 15, etc.) to achieve intelligent hemostasis management through a closed-loop control of "sensing, decision-making, and execution".

[0058] Hardware system architecture:

[0059] like Figure 9 As shown, a control circuit for a radial artery hemostatic compressor includes a microcontroller unit (MCU), control buttons 4, a display screen 3, a pressure sensor 11, a color sensor 804, an air pump 15 drive module, a pressure relief valve 16 drive module, an exhaust valve 805 drive module, and a power supply module. The signal output terminal of the control button 4 is electrically connected to the first input terminal of the MCU for inputting pressure adjustment commands to the MCU. The signal output terminal of the pressure sensor 11 is electrically connected to the second input terminal of the MCU for acquiring pressure signals within the pipeline and transmitting them to the MCU. The signal output terminal of the color sensor 804 is electrically connected to the third input terminal of the MCU for acquiring color signals within the airbag assembly 8 and transmitting them to the MCU. The MCU is connected to the air pump 15 via the air pump 15 drive module, the second output terminal is connected to the pressure relief valve 16 via the pressure relief valve 16 drive module, and the third output terminal is connected to the exhaust valve 805 via the exhaust valve 805 drive module. This is used to control the operation of the air pump 15, pressure relief valve 16, and exhaust valve 805 according to the received signals. The fourth output terminal of the MCU is connected to the display screen 3 to control the display screen 3 to display the pressure value. The power supply module is electrically connected to the MCU, control button 4, display screen 3, pressure sensor 11, color sensor 804, air pump 15 drive module, pressure relief valve 16 drive module, and exhaust valve 805 drive module respectively, for power supply.

[0060] The core architecture of the control circuit, consisting of nine functional modules, is further described below based on the physical connections and signal flow of each module:

[0061] Microcontroller Unit (MCU): The STM32L051C8T6 chip (ARM Cortex-M0 core, 32MHz) is selected, which integrates a 12-bit ADC, PWM timer and I²C / UART interface, and serves as the control center to process all input signals and output control commands.

[0062] Control button 4: Three tactile buttons (model TS-1185) are used. The button signals are debouncing by an RC filter circuit (R=10kΩ, C=100nF) and then connected to the PA0PA3 pin (first input terminal) of the MCU.

[0063] Display 3: A 0.96-inch OLED screen (SSD1306 driver, I²C interface) is selected. It is connected to the fourth output terminal of the MCU through the PB6PB7 pin to display the pressure value (accuracy ±1mmHg), working mode and fault code in real time.

[0064] Pressure sensor 11: It adopts MPXV5004G (range 0-400mmHg, accuracy ±1mmHg), and is connected to the ADC channel of the MCU (PA4 pin, second input terminal) after being connected in series with a 1kΩ current limiting resistor to collect the gas pressure signal in the first pipeline 10.

[0065] Color sensor 804: It adopts TCS34725 (RGB three-channel, spectral response 400-700nm), is connected to the third input terminal of MCU through I²C interface (PB8PB9 pin), and is installed inside the split airbag 802 to identify color changes caused by bleeding at the puncture point.

[0066] Air pump 15 drive module: It is composed of an H-bridge circuit with N-channel MOS transistors (IRF740), which receives the PWM signal output from the PB0 pin (first output terminal) of the MCU and drives the miniature air pump 15 (model PM1-00, working voltage 3-6V) to inflate.

[0067] Pressure relief valve 16 drive module: The pressure relief valve 16 is controlled by a relay (G6K-2PY-5VDC). The relay coil is driven by a transistor (2N3904) and controlled by the PB1 pin (second output terminal) of the MCU.

[0068] Exhaust valve 805 drive module: Each split airbag 802 has an exhaust valve 805 (SMC S070 series solenoid valve) with an independent drive circuit (with the same structure as the pressure relief valve 16 drive module), which is controlled by the PB2-PBn pins (third output terminal) of the MCU to realize staged exhaust.

[0069] Power module: Powered by lithium battery 6 (3.7V / 1000mAh), regulated to 3.3V by LDO chip (LP29853.3) to power MCU and sensors; boosted to 5V by boost chip (MT3608) to power air pump 15, solenoid valve and display screen 3.

[0070] Signal transmission path:

[0071] The signal flow in the control circuit follows the principle of "layered processing":

[0072] Input layer: The operation commands of control button 4, the pressure signal of pressure sensor 11, and the RGB signal of color sensor 804 are transmitted to the corresponding input terminals of MCU through hardware interfaces;

[0073] Processing layer: The MCU filters, normalizes, and performs logic operations on the input signals to generate pressure control signals and exhaust valve 805 drive signals;

[0074] Output layer: The control quantity is amplified by the drive module and drives the air pump 15, pressure relief valve 16 and exhaust valve 805 to operate. At the same time, the pressure data is displayed in real time on the OLED screen.

[0075] Core Algorithm and Parameter Design:

[0076] Pressure signal filtering algorithm: Due to airflow disturbances and sensor noise during the operation of air pump 15, the raw pressure signal needs to be filtered. A first-order low-pass filter algorithm is used:

[0077]

[0078] Parameter definition:

[0079] : Filtered pressure value at time n (unit: mmHg);

[0080] The original pressure value at time n (acquired by the MCU via a 12-bit ADC, conversion formula is...). );

[0081] : Filtering coefficient, with a value of 0.3 (determined experimentally: when α < 0.2, over-filtering leads to response delay; when α > 0.5, noise suppression is insufficient).

[0082] Implementation method: It is executed in the MCU through an interrupt service routine (sampling frequency 10Hz). The filtered data is stored in a 32-bit floating-point variable for subsequent control algorithm calls.

[0083] The pressure closed-loop control algorithm employs a PID control algorithm to achieve precise regulation of the target pressure.

[0084]

[0085] Parameter definition:

[0086] : Drive voltage of air pump 15 at time n (unit: V);

[0087] Pressure deviation (unit: mmHg), where Target pressure (set via control button 4, range 50-300 mmHg);

[0088] (proportion coefficient) (Integral coefficient) (Differential coefficients), tuned using the Ziegler-Nichols method:

[0089] Proportional segment: when At that time, the system had no overshoot;

[0090] Integral Segment: Integral Time Eliminate static errors;

[0091] Differential segment: Differential time This helps to suppress pressure fluctuations.

[0092] Constraints:

[0093] when At that time, forced (Maximum operating voltage of air pump 15);

[0094] when When this occurs, the pressure relief valve 16 is activated (instead of the air pump 15 reversing).

[0095] The color signal processing algorithm uses RGB signals collected by the 804 color sensor to identify bleeding at the puncture site (blood appears red, and the R channel value is significantly increased). Normalization processing is used to eliminate ambient light interference.

[0096]

[0097] Parameter definition:

[0098] R, G, B: Raw sensor output values ​​(0-255);

[0099] : The normalized value (0-1).

[0100] Bleeding threshold: determined through clinical trials, when... and If bleeding is detected at the puncture site, the MCU will trigger a pressurization command for the corresponding area's airbag.

[0101] The phased pressure relief control logic follows a "peripheral first, then central" approach. The control timing of the 805 exhaust valve is as follows:

[0102] Phase 1 (External Decompression): When the compression time reaches the set value (e.g., 30 minutes), the MCU controls the exhaust valve 805 of the outer ring split airbag 802 to open, and the decompression rate meets the following requirements:

[0103]

[0104] (until external pressure drops) ).

[0105] Phase 2 (Central Decompression): After a 5-minute interval, the decompression valve 805 of the central airbag is opened, and the decompression rate is the same as above, until the pressure drops to 0.

[0106] Implementation method: The exhaust valve 805 drive signal is triggered by the MCU's timer (TIM2, timing accuracy 10ms). The action status of each exhaust valve 805 is recorded by the GPIO pin level (high level to conduct).

[0107] Hardware implementation details: anti-interference design

[0108] Power supply anti-interference: A 10μF electrolytic capacitor and a 0.1μF ceramic capacitor are connected in parallel at the LDO output to suppress power supply ripple (ripple coefficient <5mV).

[0109] Signal interference immunity: The pressure sensor 11 is connected to the MCU with a shielded cable, and a 220Ω matching resistor is connected in series at the interface of the color sensor 804 to reduce electromagnetic interference;

[0110] Mechanical anti-interference: A silicone pad is installed between the control button 4 and the housing 7 to prevent accidental activation caused by the vibration of the compressor.

[0111] Security protection mechanism:

[0112] Overvoltage protection: When When the MCU immediately cuts off the power to the air pump 15 and opens the pressure relief valve 16, the display screen 3 flashes an "OVERPRESS" alarm.

[0113] Undervoltage protection: When the voltage of battery 6 is less than 3.0V, display 3 shows "LOWBAT" and automatically enters low power mode (turns off air pump 15 and only retains pressure monitoring).

[0114] Overtime protection: After continuous operation for more than 2 hours, a full pressure relief operation will be automatically performed to prevent tissue damage caused by prolonged pressure.

[0115] Workflow and Operating Instructions:

[0116] During the initialization phase (10 seconds after power-on), the MCU performs a self-test: sequentially checks the connection status of each sensor and actuator. If any abnormality is detected, the corresponding fault code is displayed (e.g., "E1" indicates a fault in pressure sensor 11).

[0117] Sensor calibration: Zero-point calibration of pressure sensor 11 (at atmospheric pressure) Set to 0), color sensor 804 white balance calibration (set reference value via white standard plate).

[0118] Compression control phase: Medical staff secure the compressor to the patient's wrist using wristband 9, ensuring the cuff assembly 8 is aligned with the puncture point; press the "START" button, and set the target pressure (e.g., 180 mmHg) using the "+" and "-" buttons; the MCU drives the air pump 15 to inflate, displaying the current pressure in real time (refresh rate 10 Hz) until the pressure is reached. The color sensor 804 continuously monitors (sampling frequency 1Hz), and if bleeding is detected ( It will automatically increase the pressure of the corresponding airbag by 10%.

[0119] Decompression phase: After the set time is reached, it will automatically enter phase 1 decompression (external airbag), and display screen 3 will show "STAGE1"; during phase 2 decompression, it will show "STAGE2" until it is completely decompressed and then shows "COMPLETE".

[0120] Performance verification and parameter specifications:

[0121] The performance of the control circuit was verified through preclinical experiments (using a simulated vascular model and a porcine radial artery puncture model) as follows:

[0122] Pressure control accuracy: Within the range of 50-300 mmHg, the deviation between the actual pressure and the target pressure is ≤ ±2 mmHg;

[0123] Response speed: from 0 to The time required is <30s, and the pressure relief response time (from the issuance of the command to the start of pressure decrease) is <100ms;

[0124] Color recognition accuracy: >95% accuracy for fresh blood (n=50 experiments);

[0125] Power consumption specifications: Standby power consumption <10mA, operating power consumption (when the air pump is running) <100mA, battery life ≥8h.

[0126] This implementation achieves precise and intelligent control of radial artery hemostasis compression through the collaborative design of hardware and algorithms, fully meeting the clinical needs for hemostasis after radial artery intervention. Those skilled in the art can reproduce this control circuit based on the above description by selecting the same type of components and programming (refer to the core code snippet in the example below).

[0127] Example: Core code snippet (C language)

[0128] / / Pressure filtering function

[0129] floatpressure_filter(floatraw_p){

[0130] staticfloatp_prev=0;

[0131] floatalpha = 0.3;

[0132] floatp_filtered=alpharaw_p+(1alpha)p_prev;

[0133] p_prev=p_filtered;

[0134] return p_filtered;

[0135] }

[0136] / / PID control function

[0137] floatpid_control(floattarget_p,floatcurrent_p){

[0138] staticfloatintegral=0;

[0139] staticfloaterror_prev=0;

[0140] floatKp=0.02,Ki=0.005,Kd=0.01;

[0141] floaterror = target_pcurrent_p;

[0142] integral += error 0.1; / / Sampling period 0.1s

[0143] floatderivative=(errorerror_prev) / 0.1;

[0144] floatu=Kperror+Kiintegral+Kdderivative;

[0145] error_prev=error;

[0146] return(u>6)?6:(u<0?0:u); / / Output limit

[0147] }

[0148] It should be noted that, in this document, the terms "including," "comprising," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or apparatus. Specific examples have been used in this document to illustrate the principles and implementation methods of the present invention. These examples are merely for the purpose of helping to understand the method and core ideas of the present invention. The above descriptions are only preferred embodiments of the present invention. It should be pointed out that, due to the limitations of written expression and the objective existence of infinite specific structures, those skilled in the art can make several improvements, modifications, or variations without departing from the principles of the present invention, and can also combine the above technical features in an appropriate manner. These improvements, modifications, variations, or combinations, or the direct application of the inventive concept and technical solution to other situations without modification, should all be considered within the scope of protection of the present invention.

Claims

1. A radial artery hemostatic compressor, characterized in that, Includes an upper cover (2) and a housing (7). A wristband (9) and an airbag assembly (8) are provided at the bottom of the housing (7). A circuit board (5) and a battery (6) are provided inside the housing (7). A control button (4) and a display screen (3) are provided on the circuit board (5). An air pump (15) and a pressure relief valve (16) are provided inside the housing (7). The air pump (15) and the pressure relief valve (16) are connected to a quick connector (12) through a third pipe (14) and a first pipe (10), respectively. The quick connector (12) is connected to the airbag assembly (8) through a second pipe (13). The airbag assembly (8) includes a support member (801) and a split airbag (802). The split airbag (802) is installed in the wristband (9) through the support member (801). The split airbag (802) is a polygonal bladder structure made of transparent material. Multiple split airbags (802) are combined in a honeycomb structure. Each split airbag... The airbag (802) can be independently inflated and deflated. The split airbag (802) is equipped with a color sensor (804), an exhaust valve (805) and a fourth pipe (803). The end of the fourth pipe (803) extending out of the split airbag (802) is equipped with a one-way valve (808). The fifth pipe (809) on the one-way valve (808) is connected to a multi-pipe connector (17). The multi-pipe connector (17) is connected to a second pipe (13). The color sensor (804) is an RGB three-channel digital sensor. It can detect the bleeding point by detecting the color change of blood seepage. When a staged depressurization operation is required, in stage 1, only the exhaust valve (805) on the outer split airbag (802) is activated, and the middle split airbag (802) maintains a certain pressure to continue to compress for hemostasis. In stage 2, the exhaust valve (805) on the middle split airbag (802) is activated, and the pressure is gradually reduced to a safe level.

2. The radial artery hemostatic compressor according to claim 1, characterized in that, The upper surface of the upper end cap (2) is provided with a transparent sheet-like protective film (1).

3. The radial artery hemostatic compressor according to claim 1, characterized in that, A pressure sensor (11) is installed on the first pipe (10).

4. The radial artery hemostatic compressor according to claim 1, characterized in that, The lower part of the wristband (9) is attached by Velcro.

5. The radial artery hemostatic compressor according to claim 1, characterized in that, A limiting seat is provided outside the air pump (15) and the pressure relief valve (16) and inside the housing (7).

6. The radial artery hemostatic compressor according to claim 1, characterized in that, The first pipe (10) is provided with an L-shaped parallel plate-shaped limiting plate on its exterior.

7. The radial artery hemostatic compressor according to claim 1, characterized in that, The color sensor (804) is externally provided with a light strip (806), and multiple LED light sources (807) are arranged around the light strip (806).

Images