Adjustable femoral artery automatic pressurization device

Abstract

The present application relates to the technical field of medical devices, and discloses an adjustable femoral artery automatic pressure device, which comprises a main shell, a position adjusting assembly is installed on the top of the main shell, a moving shell is slidably connected to the middle of the main shell, a connecting column is fixedly connected to the bottom of the moving shell, an air bag is arranged at the bottom of the connecting column, a compression head is fixedly connected to the bottom of the air bag, an angle adjusting and positioning assembly is installed on the side of the main shell, a bandage rod is arranged on the side of the angle adjusting and positioning assembly, a composite sensing module is installed in the middle of the compression head, an air pipe is arranged in the moving shell, and one end of the air pipe penetrates through the connecting column and is fixedly connected to the air hole of the air bag. By sensing the physiological signals of blood flow and hematoma formation in real time, adaptive closed-loop adjustment of compression pressure is realized, so that the hemostasis accuracy, individualization level and safety of the femoral artery automatic pressure device are improved.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to an adjustable femoral artery automatic pressure device. Background Technology

[0002] Percutaneous femoral artery puncture is one of the most widely used approaches in interventional cardiovascular and cerebrovascular procedures. After the procedure, timely, effective, and reliable compression of the puncture site is crucial for hemostasis, preventing postoperative complications such as bleeding, hematoma, and pseudoaneurysm, and ensuring patient safety. Currently, manual or mechanical compression devices are mainly used clinically for hemostasis. Mechanical compression devices, in particular, are increasingly widely used due to their ability to provide continuous and stable pressure and to free medical staff from prolonged, strenuous physical labor.

[0003] Existing mechanical femoral artery compression hemostasis devices typically include a base for fixation to the patient's body, a support structure spanning the groin region, and a compression head positioned by the support structure to apply pressure to the femoral artery puncture site. Their operating mode is generally as follows: initially, a high pressure is applied to ensure complete occlusion of blood flow; after maintaining this pressure for a period of time, the pressure is gradually reduced manually by medical personnel or automatically by the device according to a pre-set, stepwise "time-pressure" program until the compression is finally completely relieved.

[0004] While existing mechanical pressurization devices have achieved standardized operation to some extent and reduced the workload of medical staff, their inherent design concepts and working methods still leave them with some shortcomings:

[0005] First, existing devices generally lack the ability to adapt to individual differences. Their "time-pressure" procedures are essentially empirical protocols based on extensive clinical statistical data. However, in clinical practice, patients exhibit significant differences in their physiological conditions, such as coagulation function, blood pressure levels, vascular elasticity, and subcutaneous fat thickness. These factors directly affect the ease and time required for hemostasis. Applying a standardized procedure to all patients may lead to excessive compression in those with good coagulation function, causing unnecessary pain and even increasing the risk of distal limb ischemia and nerve damage; while for patients using anticoagulants or with hypertension, it may result in insufficient compression or premature decompression, leading to serious complications such as rebleeding and subcutaneous hematoma.

[0006] Secondly, the pressure reduction decision of the existing device is based on a preset time. The control system only executes the preset program in one direction. It can only monitor and control the pressure value inside the airbag. It cannot perceive the real physiological state of the tissue below the compression point, such as whether a stable thrombus has formed in the arterial rupture or whether there is slow blood seepage under the skin. This disconnect from the real physiological state makes it unable to respond in a timely and effective manner to any sudden situation during the compression process (such as the displacement of the compression point due to patient movement or blood pressure fluctuations), thus limiting its safety and reliability. Summary of the Invention

[0007] To address the shortcomings of existing technologies, this invention provides an adjustable femoral artery automatic compression device, which solves the problem that existing femoral artery automatic compression devices can only execute preset fixed programs and cannot sense the real physiological state of the compression point in real time, thus resulting in a lack of individualized adaptability and intelligent feedback in the hemostasis process.

[0008] To achieve the above objectives, the present invention provides the following technical solution: an adjustable femoral artery automatic pressurization device, comprising a main housing, a position adjustment component mounted on the top of the main housing, a movable housing slidably connected to the middle of the main housing, a connecting column fixedly connected to the bottom of the movable housing, an air bladder disposed at the bottom of the connecting column, a compression head fixedly connected to the bottom of the air bladder, an angle adjustment and positioning component mounted on the side of the main housing, a strapping rod disposed on the side of the angle adjustment and positioning component, a composite sensing module mounted in the middle of the compression head, and an air tube disposed inside the movable housing, one end of the air tube passing through the connecting column and fixed thereon. The air vents of the airbag are connected to the top of the main housing, and an upper shell is fixedly connected to the top of the main housing. A four-way connecting pipe is fixedly connected to the other end of the air tube. A pressure actuator module is installed at the connection end of the four-way connecting pipe. The composite sensing module and the pressure actuator module are connected via computer communication. The composite sensing module is used to collect physiological signals of the femoral artery region in real time. The computer is used to receive the physiological signals collected by the composite sensing module, analyze and determine the hemostasis status of the femoral artery region based on the physiological signals, and generate control commands based on the hemostasis status determination results. The pressure actuator module receives the control commands and adjusts the output pressure according to the commands.

[0009] Preferably, the position adjustment assembly includes a worm gear rotatably connected to the top of the main housing. A rotating column is rotatably connected to the top of the main housing. A worm wheel and a gear are fixedly connected to the outer side of the rotating column. The worm gear meshes with the worm wheel. A rack is fixedly connected to the side of the movable housing. The gear meshes with the rack. A rotating handle is fixedly connected to the end of the worm gear.

[0010] Preferably, a sliding plate is fixedly connected to the side of the movable shell, and a groove is provided on the top of the main shell, with the sliding plate slidably connected inside the groove.

[0011] Preferably, the angle adjustment and positioning assembly includes a rotating plate, which is rotatably connected to the side of the main housing. A strap rod is fixedly connected to the side of the rotating plate. A connecting block is slidably connected inside the main housing. A semi-circular locking block and a limiting block are fixedly connected to the end and outer side of the connecting block, respectively. A spring is provided inside the main housing. The spring contacts the end of the connecting block away from the semi-circular locking block. A semi-circular locking groove is provided on the side of the strap rod. The semi-circular locking block and the semi-circular locking groove are engaged with each other. A limiting groove is provided inside the main housing. The limiting block is slidably connected inside the limiting groove.

[0012] Preferably, a guide plate is fixedly connected to the outer side of the rotating plate, and a guide groove is provided on the inner side of the main housing, with the guide plate slidably connected inside the guide groove.

[0013] Preferably, the composite sensing module includes a piezoelectric thin film sensor and an electrode. The piezoelectric thin film sensor is disposed in the middle of the compression head, and the electrode is disposed at the bottom of the compression head. The piezoelectric thin film sensor is used to collect tissue micro-vibration signals in the femoral artery region, and the electrode is used to measure the subcutaneous tissue impedance in the femoral artery region.

[0014] Preferably, the pressure actuation module includes an air pump, a solenoid valve, and a pressure sensor, wherein the air pump, the solenoid valve, and the pressure sensor are respectively connected to the four-way connecting pipe via connecting pipes.

[0015] Preferably, the computer analyzes and determines the hemostasis status based on tissue micro-vibration signals, specifically configured to: calculate the jet flow rate index during the initial pressurization process, and determine the minimum effective hemostasis pressure based on the change in the jet flow rate index; the jet flow rate index is determined by the following formula: In the formula: JFI is the jet flow rate index, a dimensionless value or a value with a specific unit; a larger value indicates a stronger jet. PSD(f) is the power spectral density function of the acoustic signal, representing the power distribution of the signal at frequency f; f is the frequency. jet _low and f jet _high represents the pre-defined lower and upper frequency limits that uniquely characterize the sound of blood jets.

[0016] Preferably, the computer determines the hemostasis status based on subcutaneous tissue electrical impedance analysis, specifically configured as follows: during the hemostasis process, the subcutaneous tissue electrical impedance in the initial stable state is recorded as a baseline value, and continuously monitored to calculate the hematoma formation index, wherein the hematoma formation index is used to characterize the degree of deviation of the current subcutaneous tissue electrical impedance from the baseline value; the hematoma formation index is determined by the following formula: In the formula: HFI(t) is the hematoma formation index at time t, a dimensionless ratio. The larger the value, the further the tissue impedance deviates from the baseline, and the higher the risk of hematoma; Z tissue (t) represents the tissue electrical impedance value measured by the electrical impedance sensing unit at time t; Z baseline The baseline value of tissue electrical impedance is measured under the initial stable state after effective hemostasis has been confirmed; t is time.

[0017] Preferably, the adaptive adjustment of the computer during the depressurization process is specifically configured to: generate the control command based on the real-time monitoring results of the jet flow index and hematoma formation index; and generate a control command to pause or reverse the depressurization process when the jet flow index or hematoma formation index exceeds its respective preset safety threshold.

[0018] This invention provides an adjustable automatic femoral artery compression device. It has the following beneficial effects:

[0019] 1. This invention improves the applicability and fixation reliability of the device by setting up a self-locking adjustment mechanism for the angle of the bandage rod. This structure utilizes the cooperation between the rotating plate and the spring-driven semi-circular locking block to achieve rapid unlocking, smooth rotation, and stable locking of the bandage rod at any angle. Compared with the traditional fixed-angle connection method, this invention allows users to freely choose the wrapping path and fixation position of the bandage according to the different body characteristics of patients or specific clinical needs, no longer limited to a single fixation mode. This ensures that the device can be more firmly and closely fixed to the patient's body, providing a basis for subsequent precise pressure application and broadening the clinical application scope of this femoral artery automatic pressure device.

[0020] 2. This invention integrates a two-stage transmission mechanism that links a worm gear and a rack and pinion, enabling precise and convenient adjustment of the pressure head position. The operator only needs to turn the external handle; the self-locking characteristic of the worm gear mechanism stably transmits rotational motion into gear rotation, which in turn drives the rack to smoothly linearly displace the pressure head. This makes operation effortless and convenient, providing a fine adjustment capability that allows the operator to quickly and accurately align the pressure head with the tiny incision site of the femoral artery puncture. Compared to traditional manual positioning methods, this precise alignment capability is a prerequisite for ensuring the pressure effect and the accuracy of subsequent physiological signal monitoring, effectively improving the overall ease of use and effectiveness of the automatic femoral artery pressure device.

[0021] 3. This invention uses a piezoelectric thin-film sensor and bioelectrical impedance electrode to sense the blood flow status and hematoma formation below the compression point in real time, and quantifies these physiological indicators as jet flow rate index and hematoma formation index. The computer no longer relies on a fixed time step, but dynamically and intelligently adjusts the output pressure based on the real-time analysis of these two core indices. This allows the device to respond individually to the individual's real physiological response, apply appropriate pressure while ensuring effective hemostasis, and automatically complete programmed depressurization at the safest time, significantly improving the intelligence level and clinical application safety of the femoral artery automatic pressure device. Attached Figure Description

[0022] Figure 1 This is a perspective view of the present invention;

[0023] Figure 2 This is a schematic diagram of the structure of the movable shell of the present invention;

[0024] Figure 3 This is a schematic diagram of the structure of the airbag of the present invention;

[0025] Figure 4 This is a schematic diagram of the worm gear structure of the present invention;

[0026] Figure 5 This is a schematic diagram of the connecting block of the present invention;

[0027] Figure 6 This is a schematic diagram of the rotating plate of the present invention;

[0028] Figure 7 This is a schematic diagram of the device structure of the present invention.

[0029] The components are as follows: 1. Main housing; 2. Moving housing; 3. Connecting column; 4. Airbag; 5. Compression head; 6. Air tube; 7. Four-way connecting pipe; 8. Upper shell; 9. Rotating plate; 10. Strap rod; 11. Worm gear; 12. Rotating column; 13. Worm wheel; 14. Gear; 15. Rack; 16. Slide plate; 17. Slide groove; 18. Rotating handle; 19. Connecting block; 20. Semi-circular locking block; 21. Spring; 22. Semi-circular locking groove; 23. Limiting block; 24. Limiting groove; 25. Guide plate; 26. Guide groove; 27. Piezoelectric film sensor; 28. Electrode; 29. ​​Air pump; 30. Solenoid valve; 31. Pressure sensor. Detailed Implementation

[0030] The technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0031] Please see the appendix Figure 1 - Appendix Figure 3 This invention provides an adjustable femoral artery automatic pressurization device, comprising a main housing 1, a position adjustment component mounted on the top of the main housing 1, a movable housing 2 slidably connected to the middle of the main housing 1, a connecting column 3 fixedly connected to the bottom of the movable housing 2, an airbag 4 disposed at the bottom of the connecting column 3, a compression head 5 fixedly connected to the bottom of the airbag 4, an angle adjustment and positioning component mounted on the side of the main housing 1, a strapping rod 10 disposed on the side of the angle adjustment and positioning component, the strapping rod 10 connecting the strap and the pressurization device, a composite sensor module mounted in the middle of the compression head 5, and an air tube 6 disposed inside the movable housing 2, one end of the air tube 6 penetrating the connecting column 3 and fixedly connected to the air hole of the airbag 4, allowing air to enter and pressurize the airbag 4. The top of the main housing 1 is fixedly connected to the upper shell 8, which protects the structure at the top of the main housing 1. The other end of the trachea 6 is fixedly connected to the four-way connecting pipe 7. The connection end of the four-way connecting pipe 7 is equipped with a pressure actuator module. The four-way connecting pipe 7 connects the airbag 4, the trachea 6 and the pressure actuator module to the same airway. The composite sensing module and the pressure actuator module are connected via computer communication. The composite sensing module is used to collect physiological signals in the femoral artery area in real time. The computer is used to receive the physiological signals collected by the composite sensing module, analyze and determine the hemostasis status of the femoral artery area based on the physiological signals, and generate control commands based on the hemostasis status determination results. The pressure actuator module receives the control commands and adjusts the output pressure according to the commands.

[0032] Please see the appendix Figure 1 - Appendix Figure 4 In a preferred embodiment of the present invention, the position adjustment assembly includes a worm gear 11, which is rotatably connected to the top of the main housing 1. A rotating column 12 is rotatably connected to the top of the main housing 1. A worm wheel 13 and a gear 14 are fixedly connected to the outer side of the rotating column 12. The rotating column 12 causes the worm wheel 13 and the gear 14 to rotate synchronously. The worm gear 11 and the worm wheel 13 mesh with each other. By rotating the worm gear 11, the rotation of the worm wheel 13 is controlled. A rack 15 is fixedly connected to the side of the movable housing 2. The gear 14 and the rack 15 mesh with each other. The worm wheel 13 drives the gear 14 to rotate synchronously, causing the gear 14 to push the rack 15 to move. A rotating handle 18 is fixedly connected to the end of the worm gear 11. By providing the rotating handle 18, it is convenient to rotate the worm gear 11.

[0033] Please see the appendix Figure 2 and attached Figure 4 In a preferred embodiment of the present invention, a sliding plate 16 is fixedly connected to the side of the movable shell 2, and a groove 17 is provided on the top of the main shell 1. The sliding plate 16 is slidably connected inside the groove 17. The movement trajectory of the movable shell 2 is limited by the cooperation between the sliding plate 16 and the groove 17.

[0034] Please see the appendix Figure 1 Appendix Figure 5 and attached Figure 6 In a preferred embodiment of the present invention, the angle adjustment and positioning assembly includes a rotating plate 9, which is rotatably connected to the side of the main housing 1. A strap rod 10 is fixedly connected to the side of the rotating plate 9. By fixing the rotating plate 9, the position of the strap is fixed. A connecting block 19 is slidably connected inside the main housing 1. A semi-circular locking block 20 and a limiting block 23 are fixedly connected to the end and outer side of the connecting block 19, respectively. By moving the connecting block 19, the semi-circular locking block 20 and the limiting block 23 move together. The main housing 1 is provided with... Spring 21 contacts the end of connecting block 19 away from semicircular locking block 20. A semicircular locking groove 22 is provided on the side of strap rod 10. Semicircular locking block 20 and semicircular locking groove 22 are engaged with each other. The pressure generated by the cooperation of spring 21 and connecting block 19 causes semicircular locking block 20 to be forcefully engaged in semicircular locking groove 22. A limiting groove 24 is provided inside the main housing 1. Limiting block 23 is slidably connected inside the limiting groove 24. With the cooperation of limiting block 23 and limiting groove 24, connecting block 19 is prevented from detaching from main housing 1.

[0035] Please see the appendix Figure 5 and attached Figure 6 In a preferred embodiment of the present invention, a guide plate 25 is fixedly connected to the outer side of the rotating plate 9, and a guide groove 26 is provided on the inner side of the main housing 1. The guide plate 25 is slidably connected inside the guide groove 26. The trajectory of the rotating plate 9 during rotation is limited by the cooperation between the guide plate 25 and the guide groove 26.

[0036] Please see the appendix Figure 1 - Appendix Figure 3 In a preferred embodiment of the present invention, the composite sensing module includes a piezoelectric thin film sensor 27 and electrodes 28. The piezoelectric thin film sensor 27 is disposed in the middle of the compression head 5, and the electrodes 28 are disposed at the bottom of the compression head 5. Four electrodes 28 are arranged as a group, and two groups are disposed at the bottom of the compression head 5. The piezoelectric thin film sensor 27 is used to collect tissue micro-vibration signals in the femoral artery region as a physiological signal characterizing whether there is blood jet from an arterial rupture. The electrodes 28 are used to measure the subcutaneous tissue impedance in the femoral artery region as a physiological signal characterizing whether a hematoma has formed in the region.

[0037] Please see the appendix Figure 1 - Appendix Figure 3In a preferred embodiment of the present invention, the pressure execution module includes an air pump 29, a solenoid valve 30 and a pressure sensor 31, which are respectively connected to a four-way connecting pipe 7 via connecting pipes.

[0038] Please see the appendix Figure 1 and attached Figure 7 In a preferred embodiment of the present invention, the computer analyzes and determines the hemostasis status based on tissue micro-vibration signals. After the device completes initial pressurization and confirms effective preliminary hemostasis through sensing, the computer enters the "baseline calibration" stage, which is specifically configured to: calculate the jet flow rate index during the initial pressurization process, and determine the minimum effective hemostasis pressure based on the change in the jet flow rate index; the jet flow rate index is determined by the following formula: In the formula: JFI is the jet flow rate index, a dimensionless value or a value with a specific unit; a larger value indicates a stronger jet. PSD(f) is the power spectral density function of the acoustic signal, representing the power distribution of the signal at frequency f; f is the frequency. jet _low and f jet _high represents the pre-calibrated lower and upper limits of the frequency that can uniquely characterize the sound of blood jet. After the baseline value is established, the device enters the "hemostasis maintenance and monitoring" stage. In this stage, the computer periodically and continuously instructs the bioelectrical impedance sensing unit to perform real-time measurement of the subcutaneous tissue impedance in the same area to obtain the impedance value that changes over time.

[0039] Please see the appendix Figure 1 and attached Figure 7 In a preferred embodiment of the present invention, the computer determines the hemostasis status based on subcutaneous tissue impedance analysis. After the baseline value is established, the device enters the "hemostasis maintenance and monitoring" stage. In this stage, the computer periodically and continuously instructs the bioelectrical impedance sensing unit to measure the subcutaneous tissue impedance of the same area in real time to obtain the impedance value that changes over time. Subsequently, the core algorithm of the computer calculates the hematoma formation index by performing calculations on the real-time impedance value and the stored baseline value. Specifically, during the hemostasis process, the subcutaneous tissue impedance in the initial stable state is recorded as the baseline value and continuously monitored to calculate the hematoma formation index. The hematoma formation index is used to characterize the degree of deviation of the current subcutaneous tissue impedance from the baseline value. The hematoma formation index is determined by the following formula: In the formula: HFI(t) is the hematoma formation index at time t, a dimensionless ratio. The larger the value, the further the tissue impedance deviates from the baseline, and the higher the risk of hematoma; Z tissue (t) represents the tissue electrical impedance value measured by the electrical impedance sensing unit at time t; Z baseline The baseline value of tissue electrical impedance is measured under the initial stable state after effective hemostasis has been confirmed; t is time.

[0040] Please see the appendix Figure 1 and attached Figure 7 In a preferred embodiment of the present invention, the adaptive adjustment of the computer during the depressurization process is specifically configured as follows: generating control commands based on real-time monitoring results of the jet flow index and hematoma formation index; when the jet flow index or hematoma formation index exceeds its respective preset safety threshold, generating control commands to pause or reverse the depressurization process, transmitting the control commands to the pressure execution module, and driving the air pump 29 and solenoid valve 30 according to the commands to perform dynamic depressurization.

[0041] Working principle: When binding the pressure device, determine the angle to be adjusted for the two binding rods. By applying rotational force to the rotating plate, the rotating plate squeezes the semi-circular locking block, causing it to move inward and disengage from the semi-circular locking groove. After the binding rod rotates to the correct position, the pressure applied by the spring to the connecting block causes the semi-circular locking block to move outward and lock into the semi-circular locking groove, fixing the current angle position of the binding rod. Then, the binding strap is passed through the binding rod to fix the binding strap in the appropriate position. The position of the binding rod can be freely rotated to fix the binding strap in other positions to adapt to patients of different body types and improve the applicability of the device.

[0042] After the strap is attached, the worm gear is controlled by rotating the handle, which rotates the worm wheel. The rotated worm wheel, through the rotating column, drives the gear to rotate together. The rotating gear pushes the rack, causing the movable shell to move, thus achieving fine adjustment of the position of the pressure head. This allows the pressure head to be quickly, conveniently, and accurately aligned with the puncture wound, effectively improving the convenience of pressurization.

[0043] The micro-vibration signals of the femoral artery region and the subcutaneous tissue impedance are transmitted to the computer via a piezoelectric thin-film sensor and electrodes. The computer calculates the jet flow index and hematoma formation index using these two sets of data. When the jet flow index or hematoma formation index exceeds its respective preset safety threshold, the computer generates a control command to pause or reverse the depressurization process and sends it to the pressure execution module. The pressure execution module controls the air pump and solenoid valve to realize the depressurization process. This eliminates reliance on a preset, fixed "time-pressure" program. Instead, it dynamically adjusts the output pressure by detecting the blood flow status and hematoma formation, so as to apply the most appropriate pressure while ensuring effective hemostasis and automatically complete the programmed depressurization at the safest time.

[0044] Although embodiments of the invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the invention, the scope of which is defined by the appended claims and their equivalents.

Claims

1. An adjustable femoral artery automatic pressurization device, comprising a main housing (1), characterized in that, A position adjustment assembly is installed on the top of the main housing (1). A movable housing (2) is slidably connected to the middle of the main housing (1). A connecting column (3) is fixedly connected to the bottom of the movable housing (2). An airbag (4) is provided at the bottom of the connecting column (3). A compression head (5) is fixedly connected to the bottom of the airbag (4). An angle adjustment positioning assembly is installed on the side of the main housing (1). A strap rod (10) is provided on the side of the angle adjustment positioning assembly. A composite sensing module is installed in the middle of the compression head (5). The composite sensing module includes a piezoelectric thin film sensor (27) and an electrode (28). The piezoelectric thin film sensor (27) is located in the middle of the compression head (5). The electrode (28) is located at the bottom of the compression head (5). The piezoelectric thin film sensor (27) is used to collect tissue micro-vibration signals in the femoral artery region. The electrode (28) is used to measure the subcutaneous tissue impedance in the femoral artery region. A trachea (6) is provided inside the movable housing (2). One end of the air tube (6) passes through the connecting post (3) and is fixedly connected to the air hole of the air bag (4). The top of the main housing (1) is fixedly connected to the upper shell (8). The other end of the air tube (6) is fixedly connected to the four-way connecting pipe (7). The connection end of the four-way connecting pipe (7) is equipped with a pressure execution module. The pressure execution module includes an air pump (29), a solenoid valve (30) and a pressure sensor (31). The air pump (29), the solenoid valve (30) and the pressure sensor (31) are respectively connected to the four-way connecting pipe (7) through the connecting pipe. The composite sensing module and the pressure execution module are connected through computer communication. The composite sensing module is used to collect physiological signals of the femoral artery area in real time. The computer is used to receive the physiological signals collected by the composite sensing module, analyze and determine the hemostasis status of the femoral artery area based on the physiological signals, and generate control commands according to the hemostasis status determination results. The pressure execution module receives the control commands and adjusts the output pressure according to the commands. The position adjustment assembly includes a worm gear (11), which is rotatably connected to the top of the main housing (1). A rotating column (12) is rotatably connected to the top of the main housing (1). A worm wheel (13) and a gear (14) are fixedly connected to the outside of the rotating column (12). The worm gear (11) meshes with the worm wheel (13). A rack (15) is fixedly connected to the side of the movable housing (2). The gear (14) meshes with the rack (15). A rotating handle (18) is fixedly connected to the end of the worm gear (11). The computer analyzes and determines the hemostasis status based on tissue micro-vibration signals. Specifically, it is configured to: calculate the jet flow rate index during the initial pressurization process, and determine the minimum effective hemostasis pressure based on the change in the jet flow rate index. The jet flow rate index is determined by the following formula: ; In the formula: The jet flow rate index is a dimensionless value or a value with a specific unit; the larger the value, the stronger the jet. Let be the power spectral density function of the acoustic signal, representing the signal at frequency . Power distribution on; For frequency; and These are the pre-calibrated lower and upper frequency limits that uniquely characterize the sound of blood jets; The computer determines the hemostasis status based on subcutaneous tissue electrical impedance analysis, specifically configured to: during the hemostasis process, record the subcutaneous tissue electrical impedance in the initial stable state as a baseline value, and continuously monitor it to calculate the hematoma formation index, wherein the hematoma formation index is used to characterize the degree of deviation of the current subcutaneous tissue electrical impedance from the baseline value; The hematoma formation index is determined by the following formula: ; In the formula: for The hematoma formation index at any given time is a dimensionless ratio. The higher the value, the further the tissue impedance deviates from the baseline, and the higher the risk of hematoma. for The tissue electrical impedance value measured by the electrical impedance sensing unit at any time; The baseline value of tissue electrical impedance is measured under the initial stable condition after effective hemostasis has been confirmed. For time; The adaptive adjustment of the computer during the bucking process is specifically configured as follows: The control command is generated based on the real-time monitoring results of the jet flow rate index and the hematoma formation index; when the jet flow rate index or the hematoma formation index exceeds its respective preset safety threshold, a control command is generated to pause or reverse the depressurization process.

2. The adjustable femoral artery automatic pressurization device according to claim 1, characterized in that, The movable shell (2) is fixedly connected to a sliding plate (16) on its side, and the top of the main shell (1) is provided with a sliding groove (17), and the sliding plate (16) is slidably connected inside the sliding groove (17).

3. The adjustable femoral artery automatic pressurization device according to claim 2, characterized in that, The angle adjustment and positioning assembly includes a rotating plate (9), which is rotatably connected to the side of the main housing (1). A strap rod (10) is fixedly connected to the side of the rotating plate (9). A connecting block (19) is slidably connected inside the main housing (1). A semi-circular locking block (20) and a limiting block (23) are fixedly connected to the end and the outside of the connecting block (19), respectively. A spring (21) is provided inside the main housing (1). The spring (21) contacts the end of the connecting block (19) away from the semi-circular locking block (20). A semi-circular locking groove (22) is provided on the side of the strap rod (10). The semi-circular locking block (20) and the semi-circular locking groove (22) are locked together. A limiting groove (24) is provided inside the main housing (1). The limiting block (23) is slidably connected inside the limiting groove (24).

4. The adjustable femoral artery automatic pressurization device according to claim 3, characterized in that, A guide plate (25) is fixedly connected to the outer side of the rotating plate (9), and a guide groove (26) is provided on the inner side of the main housing (1). The guide plate (25) is slidably connected inside the guide groove (26).

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