Adjustable femoral artery automatic pressurizing device

Abstract

The invention relates to the technical field of medical instruments, and discloses an adjustable femoral artery automatic pressurizing device which comprises a main shell, a position adjusting assembly is mounted at 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, and an air outlet is formed in the middle of the air bag. A compression head is fixedly connected to the bottom of the air bag, an angle adjusting and positioning assembly is installed on the side face of the main shell, a bandage rod is arranged on the side face of the angle adjusting and positioning assembly, a composite sensing module is installed in the middle of the compression head, and an air pipe is arranged in the movable shell. 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 physiological signals formed by blood flow and hematoma in real time, self-adaptive closed-loop adjustment of compression pressure is realized, so that hemostasis accuracy, individualized level and safety of the automatic femoral artery pressurizing device are improved.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, in particular to an adjustable femoral artery automatic pressurizing device. Background Art

[0002] Percutaneous femoral artery puncture is one of the most widely used access methods in cardiovascular interventional diagnosis and treatment. After the operation, timely, effective and reliable compression and hemostasis of the arterial puncture site is a key link in preventing complications such as postoperative bleeding, hematoma, and pseudoaneurysm, and ensuring patient safety. Currently, manual compression or mechanical compression devices are mainly used in clinical practice to stop bleeding. Among them, mechanical compression devices have been increasingly widely used because they can provide continuous and stable pressure and can liberate medical staff from long-term and high-intensity physical labor.

[0003] Existing mechanical femoral artery compression hemostasis devices typically consist of a base for securing to the patient's body, a support structure that spans the groin area, and a compression head positioned by the support structure to apply pressure to the femoral artery puncture site. Their typical operating mode is to initially apply high pressure to ensure complete blood flow occlusion. After a period of maintenance, the pressure is gradually reduced, either manually by the medical staff or automatically by the device, according to a pre-set, step-by-step "time-pressure" process, until it is completely released.

[0004] Although the mechanical compression device in the prior art has achieved standardized operation to a certain extent and reduced the labor intensity of medical staff, its inherent design concept and working method still have some shortcomings:

[0005] First, existing devices generally lack the ability to adapt to individual differences. The "time-pressure" procedure they use is essentially an empirical scheme based on a large amount of clinical statistical data. However, in clinical practice, there are significant differences in the physiological conditions of different patients, such as coagulation function, blood pressure levels, vascular elasticity, subcutaneous fat thickness, etc. These factors directly affect the difficulty and time required for hemostasis. Applying a standardized procedure to all patients may lead to excessive compression for patients with good coagulation function, causing unnecessary pain and even increasing the risk of distal limb ischemia and nerve damage; for patients using anticoagulants or suffering from hypertension, it may lead to insufficient compression or premature withdrawal of pressure, thereby causing serious complications such as rebleeding and subcutaneous hematoma.

[0006] Secondly, the existing device's blood pressure reduction decision is based on a preset time, and the control system only executes the preset program unidirectionally. 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 the arterial rupture has formed a stable thrombus, whether there is slow blood seepage under the skin, and other key information. It is disconnected from the real physiological state, making it unable to respond promptly and effectively to any emergencies during the compression process (such as compression point displacement caused by patient movement, blood pressure fluctuations, etc.), limiting its safety and reliability. Summary of the Invention

[0007] In response to the shortcomings of the existing technology, the present invention provides an adjustable femoral artery automatic pressurization device, which solves the problem that the existing femoral artery automatic pressurization device can only execute a preset fixed program and cannot perceive the true physiological state of the pressure point in real time, resulting in a lack of individualized adaptability and intelligent feedback in the hemostasis process.

[0008] To achieve the above objectives, the present invention is implemented through the following technical solutions: an adjustable femoral artery automatic pressurization device, comprising a main shell, a position adjustment component is installed on the top of the main shell, a movable shell is slidably connected to the middle of the main shell, a connecting column is fixedly connected to the bottom of the movable shell, an air bag is provided at the bottom of the connecting column, a compression head is fixedly connected to the bottom of the air bag, an angle adjustment positioning component is installed on the side of the main shell, a strap rod is provided on the side of the angle adjustment positioning component, a composite sensor module is installed in the middle of the compression head, a trachea is provided inside the movable shell, one end of the trachea passes through the connecting column and is fixed The air hole of the airbag is connected, the top of the main shell is fixedly connected to the upper shell, the other end of the trachea is fixedly connected to a four-way connecting tube, the connecting end of the four-way connecting tube is installed with a pressure execution module, the composite sensing module is connected to the pressure execution module 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 state of the femoral artery area based on the physiological signals, and generate control instructions according to the determination result of the hemostasis state, the pressure execution module receives the control instructions and adjusts the output pressure according to the instructions.

[0009] Preferably, the position adjustment assembly includes a worm, which is rotatably connected to the top of the main housing, and the top of the main housing is rotatably connected to a rotating column, and a worm wheel and a gear are fixedly connected to the outside of the rotating column, and the worm and the worm wheel are meshed with each other, and the side of the movable shell is fixedly connected to a rack, and the gear and the rack are meshed with each other, and the end of the worm is fixedly connected to a rotating handle.

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

[0011] Preferably, the angle adjustment positioning assembly includes a rotating plate, which is rotatably connected to the side of the main shell, and the side of the rotating plate is fixedly connected to a strap rod, and the interior of the main shell is slidably connected to a connecting block, and the end and outer side of the connecting block are respectively fixedly connected to a semicircular clamping block and a limit block, and a spring is provided inside the main shell, and the spring contacts one end of the connecting block away from the semicircular clamping block, and a semicircular clamping groove is provided on the side of the strap rod, and the semicircular clamping block and the semicircular clamping groove are clamped with each other, and a limiting groove is provided inside the main shell, and the limit block is slidably connected to the inside of the limiting groove.

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

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

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

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

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

[0017] Preferably, the computer is configured to adaptively adjust during the depressurization process by: generating the control instruction based on the real-time monitoring results of the jet flow index and the hematoma formation index; and generating a control instruction to pause or reverse the depressurization process when the jet flow index or the hematoma formation index exceeds their respective preset safety thresholds.

[0018] The present invention provides an adjustable femoral artery automatic pressurization device, which has the following beneficial effects:

[0019] 1. The present invention improves the applicability and fixation reliability of the device by providing a self-locking adjustment mechanism for the angle of the strap rod. The structure utilizes the cooperation between the rotating plate and the spring-driven semicircular block to achieve rapid unlocking, smooth rotation and firm locking of the strap rod at any angle. Compared with the traditional fixed-angle connection method, the present invention allows users to freely choose the winding path and fixing position of the strap according to the body characteristics of different patients or specific clinical needs, and is no longer limited to a single fixing mode, ensuring that the device can be fixed to the patient's body more firmly and more snugly, providing a basis for subsequent precise pressurization, and broadening the clinical applicability of the femoral artery automatic pressurization device.

[0020] 2. The present invention realizes precise and convenient adjustment of the position of the compression head by integrating a two-stage transmission mechanism in which a worm gear is linked with a gear rack. The operator only needs to turn the external handle to stably transmit the rotational motion into the rotation of the gear through the self-locking characteristics of the worm gear mechanism, and then drive the rack to drive the compression head to perform smooth linear displacement. The operation is labor-saving and convenient, and provides a fine adjustment capability, allowing the operator to quickly and accurately align the compression head with the tiny wound of the femoral artery puncture. Compared with the traditional manual positioning method, this precise alignment capability is the prerequisite for ensuring the pressurization effect and the accuracy of subsequent physiological signal monitoring, effectively improving the overall convenience and effectiveness of the femoral artery automatic pressurization device.

[0021] 3. The present invention uses piezoelectric film sensors and bioelectrical impedance electrodes to sense the blood flow status and hematoma formation below the compression point in real time, and quantify these physiological indicators into a jet flow index and a hematoma formation index. The computer no longer relies on a fixed time ladder, but dynamically and intelligently adjusts the output pressure based on real-time analysis of these two core indexes, so that the device can make an individualized response to the individual's real physiological reaction, apply appropriate pressure while ensuring effective hemostasis, and automatically complete programmed blood pressure reduction at the safest time, significantly improving the intelligence level and clinical application safety of the femoral artery automatic pressurization device. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] Figure 1 A perspective view of the present invention;

[0023] Figure 2 It is a structural schematic diagram of the mobile shell of the present invention;

[0024] Figure 3 Schematic diagram of the structure of the airbag of the present invention;

[0025] Figure 4 It is a structural schematic diagram of the worm of the present invention;

[0026] Figure 5 It is a structural schematic diagram of the connection block of the present invention;

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

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

[0029] Among them, 1. Main shell; 2. Moving shell; 3. Connecting column; 4. Airbag; 5. Compression head; 6. Air pipe; 7. Four-way connecting pipe; 8. Upper shell; 9. Rotating plate; 10. Strap rod; 11. Worm; 12. Rotating column; 13. Worm gear; 14. Gear; 15. Rack; 16. Slide plate; 17. Slide groove; 18. Rotating handle; 19. Connecting block; 20. Semicircular block; 21. Spring; 22. Semicircular slot; 23. Limit block; 24. Limit slot; 25. Guide plate; 26. Guide slot; 27. Piezoelectric film sensor; 28. Electrode; 29. Air pump; 30. Solenoid valve; 31. Pressure sensor. DETAILED DESCRIPTION

[0030] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the drawings in the specification of the present invention. Obviously, the embodiments described are only some embodiments of the present invention, not all embodiments. All other embodiments obtained by ordinary technicians in this field based on the embodiments of the present invention without making any creative efforts shall fall within the scope of protection of the present invention.

[0031] Please see the attached Figure 1 -Attached Figure 3 An embodiment of the present invention provides an adjustable femoral artery automatic pressurizing device, comprising a main shell 1, a position adjustment component installed on the top of the main shell 1, a movable shell 2 slidably connected to the middle of the main shell 1, a connecting column 3 fixedly connected to the bottom of the movable shell 2, an air bag 4 is provided at the bottom of the connecting column 3, a compression head 5 is fixedly connected to the bottom of the air bag 4, an angle adjustment positioning component is installed on the side of the main shell 1, a strap rod 10 is provided on the side of the angle adjustment positioning component, a strap and a pressurizing device are connected through the strap rod 10, a composite sensor module is installed in the middle of the compression head 5, an trachea 6 is provided inside the movable shell 2, one end of the trachea 6 passes through the connecting column 3 and is fixedly connected to the air hole of the air bag 4, and air is introduced through the trachea 6 to inflate and pressurize the air bag 4 The top of the main shell 1 is fixedly connected with an upper shell 8, and the upper shell 8 is used to protect the structure of the top of the main shell 1. The other end of the trachea 6 is fixedly connected with a four-way connecting tube 7. The connecting end of the four-way connecting tube 7 is installed with a pressure execution module. The four-way connecting tube 7 is used to connect the airbag 4, the trachea 6 and the pressure execution module to the same air path. 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 state of the femoral artery area based on the physiological signals, and generate control instructions according to the determination result of the hemostasis state. The pressure execution module receives the control instructions and adjusts the output pressure according to the instructions.

[0032] Please see the attached Figure 1 -Attached Figure 4 In a preferred embodiment of the present invention, the position adjustment assembly includes a worm 11, which is rotatably connected to the top of the main housing 1, and the top of the main housing 1 is rotatably connected to a rotating column 12. A worm wheel 13 and a gear 14 are fixedly connected to the outside of the rotating column 12. The worm wheel 13 and the gear 14 rotate synchronously through the rotating column 12. The worm 11 and the worm wheel 13 are engaged with each other. The rotation of the worm wheel 13 is controlled by rotating the worm 11. A rack 15 is fixedly connected to the side of the movable shell 2, and the gear 14 is engaged with the rack 15. The worm wheel 13 rotates synchronously with the gear 14, so that the gear 14 pushes the rack 15 to move. The end of the worm 11 is fixedly connected to a rotating handle 18. By setting the rotating handle 18, it is convenient to rotate the worm 11.

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

[0034] Please see the attached Figure 1 , Attachment Figure 5 and attached Figure 6 In a preferred embodiment of the present invention, the angle adjustment positioning assembly includes a rotating plate 9, which is rotatably connected to the side of the main shell 1. The side of the rotating plate 9 is fixedly connected to the strap rod 10. By fixing the rotating plate 9, the position of the strap is fixed. The interior of the main shell 1 is slidably connected to a connecting block 19. The end and the outer side of the connecting block 19 are respectively fixedly connected to a semicircular card block 20 and a limit block 23. By moving the connecting block 19, the semicircular card block 20 moves together with the limit block 23. The interior of the main shell 1 is provided with Spring 21, the spring 21 contacts one end of the connecting block 19 away from the semicircular block 20, and a semicircular groove 22 is provided on the side of the strap rod 10. The semicircular block 20 and the semicircular groove 22 are clamped with each other. The pressure generated by the cooperation of the spring 21 and the connecting block 19 causes the semicircular block 20 to be subjected to force and be clamped into the semicircular groove 22. A limiting groove 24 is provided inside the main shell 1, and the limiting block 23 is slidably connected to the inside of the limiting groove 24. Under the cooperation of the limiting block 23 and the limiting groove 24, the connecting block 19 is prevented from separating from the main shell 1.

[0035] Please see the attached 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 opened on the inner side of the main shell 1. The guide plate 25 is slidably connected to the inside of the guide groove 26. The cooperation between the guide plate 25 and the guide groove 26 limits the trajectory of the rotating plate 9 during rotation.

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

[0037] Please see the attached Figure 1 -Attached 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, and the air pump 29, the solenoid valve 30 and the pressure sensor 31 are respectively connected to the four-way connecting pipe 7 through connecting pipes.

[0038] Please see the attached Figure 1 and attached Figure 7 In a preferred embodiment of the present invention, a computer analyzes and determines the hemostatic state based on tissue microvibration signals. After the device completes initial pressurization and confirms through sensing that effective initial hemostasis has been achieved, the computer enters a "baseline calibration" phase. Specifically, the computer is configured to calculate the jet flow index during the initial pressurization process and determine the minimum effective hemostatic pressure based on changes in the jet flow index. The jet flow index is determined by the following formula: Where: JFI is the jet flow index, a dimensionless or unit-specific value, the larger the value, the stronger the jet; PSD(f) is the power spectral density function of the acoustic signal, which represents the power distribution of the signal at frequency f; f is the frequency; f jet _low and f jet _high is the pre-calibrated lower and upper frequency limits that can uniquely characterize the sound of blood jetting. After the baseline value is established, the device enters the "hemostasis maintenance and monitoring" stage. During this stage, the computer will periodically and continuously instruct the bioelectrical impedance sensor unit to measure the electrical impedance of the subcutaneous tissue in the same area in real time to obtain the impedance value that changes with time.

[0039] Please see the attached Figure 1 and attached Figure 7 In a preferred embodiment of the present invention, a computer analyzes and determines the hemostasis state based on the electrical impedance of the subcutaneous tissue. After the baseline value is established, the device enters the "hemostasis maintenance and monitoring" stage. During this stage, the computer periodically and continuously instructs the bioelectrical impedance sensing unit to measure the electrical impedance of the subcutaneous tissue in the same area in real time to obtain impedance values that change over time. Subsequently, the computer's core algorithm calculates the impedance values obtained in real time with the stored baseline values to calculate the hemorrhage formation index. Specifically, the configuration is as follows: during the hemostasis process, the electrical impedance of the subcutaneous tissue in the initial stable state is recorded as the baseline value, and continuously monitored to calculate the hemorrhage formation index, wherein the hemorrhage formation index is used to represent the degree of deviation of the current electrical impedance of the subcutaneous tissue from the baseline value; the hemorrhage formation index is determined by the following formula: Where: HFI(t) is the hematoma formation index at time t, a dimensionless ratio. The larger the value, the farther the tissue impedance deviates from the baseline, and the higher the hematoma risk; Z tissue (t) is the tissue electrical impedance value measured by the electrical impedance sensing unit at time t; Z baseline is the baseline value of tissue electrical impedance measured in the initial stable state after effective hemostasis is confirmed; t is time.

[0040] Please see the attached Figure 1 and attached Figure 7 In a preferred embodiment of the present invention, the computer is configured to adaptively adjust the pressure reduction process in the following manner: generate control instructions based on the real-time monitoring results of the jet flow index and the hematoma formation index; when the jet flow index or the hematoma formation index exceeds their respective preset safety thresholds, generate control instructions to pause or reverse the pressure reduction process, and transmit the control instructions to the pressure execution module, which drives the air pump 29 and the solenoid valve 30 according to the instructions to perform dynamic pressure reduction.

[0041] Working principle: When binding the pressure device, determine the angle to which the two strap rods need to be adjusted, and by applying rotational force to the rotating plate, the rotating plate squeezes the semicircular block, causing it to move inward and out of the semicircular slot. When the strap rod is rotated into place, the pressure applied to the connecting block by the spring causes the semicircular block to move outward under force and snap into the semicircular slot, fixing the current angle position of the strap rod. Then, pass the strap through the strap rod and fix the strap in the appropriate position. The position of the fixed strap rod can be rotated freely and the strap can be tied to other positions to adapt to patients of different body shapes and improve the applicability of the device.

[0042] After tying the strap, the worm is controlled by rotating the handle to rotate the worm wheel. The rotated worm wheel rotates with the gear through the rotating column. The rotating gear pushes the rack to move the movable shell, thereby achieving fine adjustment of the position of the compression head, so that the compression head can be quickly, conveniently and accurately aligned with the puncture wound, effectively improving the convenience of using pressure.

[0043] The tissue micro-vibration signal and subcutaneous tissue electrical impedance in the femoral artery area are transmitted to the computer through piezoelectric film sensors and electrodes. The computer calculates the jet flow index and hematoma formation index respectively through these two sets of data. When the jet flow index or hematoma formation index exceeds their respective preset safety thresholds, the computer will generate a control instruction to pause or reverse the pressure reduction process and send it to the pressure execution module. The pressure execution module realizes the pressure reduction process by controlling the air pump and solenoid valve. It no longer relies on the preset and fixed "time-pressure" program, but dynamically adjusts the output pressure by detecting the blood flow status and hematoma formation, so as to achieve the most appropriate pressure while ensuring effective hemostasis, and automatically complete the programmed pressure reduction at the safest time.

[0044] While embodiments of the present invention have been shown and described, it will be appreciated by those skilled in the art that various changes, modifications, substitutions, and variations may be made to these embodiments without departing from the principles and spirit of the invention, and that the scope of the invention 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 component is installed on the top of the main shell (1), a movable shell (2) is slidably connected to the middle of the main shell (1), a connecting column (3) is fixedly connected to the bottom of the movable shell (2), an air bag (4) is provided at the bottom of the connecting column (3), a compression head (5) is fixedly connected to the bottom of the air bag (4), an angle adjustment positioning component is installed on the side of the main shell (1), a strap rod (10) is provided on the side of the angle adjustment positioning component, a composite sensor module is installed in the middle of the compression head (5), an air pipe (6) is provided inside the movable shell (2), one end of the air pipe (6) passes through the connecting column (3) and is fixedly connected to the air bag (4), the top of the main shell (1) is fixedly connected to the upper shell (8), the other end of the trachea (6) is fixedly connected to the four-way connecting pipe (7), the connecting end of the four-way connecting pipe (7) is installed with a pressure execution module, the composite sensing module is connected to the pressure execution module 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 state of the femoral artery area based on the physiological signals, and generate control instructions according to the determination result of the hemostasis state, the pressure execution module receives the control instructions and adjusts the output pressure according to the instructions.

2. The adjustable femoral artery automatic pressurization device according to claim 1, characterized in that: The position adjustment assembly includes a worm (11), the worm (11) is rotatably connected to the top of the main housing (1), the top of the main housing (1) is rotatably connected to a rotating column (12), the outer side of the rotating column (12) is fixedly connected to a worm wheel (13) and a gear (14), the worm (11) and the worm wheel (13) are meshed with each other, the side of the movable housing (2) is fixedly connected to a rack (15), the gear (14) and the rack (15) are meshed with each other, and the end of the worm (11) is fixedly connected to a rotating handle (18).

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

4. The adjustable femoral artery automatic pressurization device according to claim 3, characterized in that: The angle adjustment positioning assembly comprises a rotating plate (9), the rotating plate (9) is rotatably connected to the side of the main shell (1), the side of the rotating plate (9) is fixedly connected to the strap rod (10), the interior of the main shell (1) is slidably connected to a connecting block (19), the end and the outer side of the connecting block (19) are respectively fixedly connected to a semicircular clamping block (20) and a limiting block (23), a spring (21) is provided inside the main shell (1), the spring (21) is in contact with an end of the connecting block (19) away from the semicircular clamping block (20), a semicircular clamping groove (22) is provided on the side of the strap rod (10), the semicircular clamping block (20) and the semicircular clamping groove (22) are mutually clamped, a limiting groove (24) is provided inside the main shell (1), and the limiting block (23) is slidably connected to the interior of the limiting groove (24).

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

6. The adjustable femoral artery automatic pressurization device according to claim 5, characterized in that: The composite sensing module comprises a piezoelectric film sensor (27) and an electrode (28), wherein the piezoelectric film sensor (27) is arranged in the middle of the compression head (5), and the electrode 28 is arranged at the bottom of the compression head (5), the piezoelectric film sensor (27) is used to collect tissue micro-vibration signals in the femoral artery area, and the electrode (28) is used to measure the electrical impedance of subcutaneous tissue in the femoral artery area.

7. The adjustable femoral artery automatic pressurization device according to claim 6, characterized in that: The pressure execution module comprises an air pump (29), a solenoid valve (30) and a pressure sensor (31), wherein the air pump (29), the solenoid valve (30) and the pressure sensor (31) are respectively connected to the four-way connecting pipe (7) via connecting pipes.

8. The adjustable femoral artery automatic pressurization device according to claim 7, characterized in that: The computer analyzes and determines the hemostasis state based on the tissue micro-vibration signal, and is specifically configured to: calculate the jet flow index during the initial pressurization process, and determine the minimum effective hemostasis pressure based on the change of the jet flow index; The jet flow index is determined by the following formula: Where: JFI is the jet flow index, a dimensionless or unit-specific value, the larger the value, the stronger the jet; PSD(f) is the power spectral density function of the acoustic signal, which represents the power distribution of the signal at frequency f; f is the frequency; f jet _low and f jet _high is the pre-calibrated lower and upper frequency limits that can uniquely characterize the blood jet sound.

9. The adjustable femoral artery automatic pressurization device according to claim 8, characterized in that: The computer analyzes and determines the hemostasis state based on the electrical impedance of the subcutaneous tissue, and is specifically configured to: during the hemostasis process, record the electrical impedance of the subcutaneous tissue in an initial stable state as a baseline value, and continuously monitor to calculate a hematoma formation index, wherein the hematoma formation index is used to represent the degree of deviation of the current electrical impedance of the subcutaneous tissue from the baseline value; The hematoma formation index was determined by the following formula: Where: HFI(t) is the hematoma formation index at time t, a dimensionless ratio. The larger the value, the farther the tissue impedance deviates from the baseline, and the higher the hematoma risk; Z tissue (t) is the tissue electrical impedance value measured by the electrical impedance sensing unit at time t; Z baseline is the baseline value of tissue electrical impedance measured in the initial stable state after effective hemostasis is confirmed; t is time.

10. The adjustable femoral artery automatic pressurization device according to claim 9, characterized in that: The computer is configured to perform adaptive adjustments during the depressurization process, and is specifically configured to: generate the control instructions based on the real-time monitoring results of the jet flow index and the hematoma formation index; and generate control instructions to pause or reverse the depressurization process when the jet flow index or the hematoma formation index exceeds their respective preset safety thresholds.

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