Compression hemostasis device after femoral artery puncture

Abstract

The present application relates to a kind of intelligent compression hemostasis device after femoral artery puncture, including probe, wristwatch is formed by using steel band to connect the both ends of probe, probe is buckled on dorsum pedis pulse, generates electric signal into the signal acquisition module of intelligent control system, after amplification by signal acquisition module, it is transferred to analysis module and is converted into pressure change wave, the average peak value of a period of pressure change wave is selected to obtain pressure value input control module, pressure value is converted into motor rotation turns, motor controls screw rod in and out screw sleeve, screw rod lower end is connected with pressing head, the pressing head includes silica gel sleeve connected with screw rod and lower pressing plate.According to the lowest sustained beat of dorsum pedis pulse Intensity guarantee lower limb blood supply condition is good, again under this premise, obtain the best compression hemostasis Intensity, can obtain the best compression hemostasis effect, and in the process of compression hemostasis, according to the physical sign of patient, dynamic best compression hemostasis effect is obtained by continuous adjustment.

Description

Technical Field

[0001] This invention relates to the field of medical devices, and more particularly to a device for compression hemostasis after femoral artery puncture. Background Technology

[0002] Interventional surgery is an important medical procedure. When femoral artery puncture is involved, the catheter needs to be removed after the procedure. During catheter removal, pressure hemostasis is required. A medical specialist needs to apply pressure at the puncture site to achieve hemostasis and closure of the arterial puncture site. This process takes about 20 minutes. While applying pressure, it is also necessary to maintain a low dorsalis pedis pulse rate—that is, to maintain the most basic blood supply to the tissues downstream of the puncture site. The strength of the dorsalis pedis pulse is inversely proportional to the amount of pressure applied at the puncture site. The best hemostasis effect after femoral artery puncture is achieved when the pressure applied at the puncture site is greater and the dorsalis pedis pulse rate is lower.

[0003] Most existing mechanical pressure hemostasis devices for femoral artery puncture achieve hemostasis by manually adjusting the pressure at the puncture site while observing the blood supply to the downstream tissues. This process requires repeated manual intervention, which is not only labor-intensive but also demands a high level of expertise from medical personnel. A few pressure hemostasis devices that use infrared temperature detection to assess blood flow have also emerged. However, infrared temperature detection can only detect the presence or absence of blood flow and cannot accurately assess its condition. Furthermore, the femoral artery is located deep within the body, and differences in tissue composition and body temperature mean that these infrared-based pressure hemostasis devices, which intelligently adjust pressure based on blood flow assessment, are not very effective after femoral artery puncture. Therefore, this type of device is rarely seen. Summary of the Invention

[0004] The purpose of this invention is to provide an intelligent compression hemostasis device after femoral artery puncture that can intelligently adjust the compression pressure, in order to solve the problem that the inability to adjust the compression pressure alone leads to poor compression hemostasis effect.

[0005] The technical solution adopted in this invention is: an intelligent compression hemostasis device after femoral artery puncture, comprising a dorsalis pedis pulse strength detector, wherein the dorsalis pedis pulse strength detector includes an inductive pressure transducer, the inductive pressure transducer comprising a pair of magnetically conductive housings, each housing containing an inductive coil, an elastic diaphragm being clamped between the two housings, the two inductive coils and two non-inductive resistors in a dynamic pressure measuring instrument forming a test bridge, a metal bowl being added to the pressure receiving port of the inductive pressure transducer, the top of the bowl having a circular hole communicating with the air gap of the transducer, forming a pulse-taking probe, the two ends of the probe being connected by a steel band to form a wristwatch-shaped dorsalis pedis pulse strength detector; it also includes a compression device, the compression device comprising an arc-shaped fixing plate acting on the lower part of the patient's thigh, the fixing plate being connected to a threaded sleeve acting on the upper part of the patient's thigh via a connecting rod, and a power cylinder Installed above the threaded sleeve, a motor is installed in the power cylinder. The motor drives the screw to move up and down in the threaded sleeve. The lower end of the screw is connected to a pressing head for pressing the puncture site. It also includes an intelligent control system, which includes a signal acquisition module, an analysis module, and a control module. The signal acquisition module receives the voltage signal wave generated by the test bridge in the dorsalis pedis pulse strength detector, amplifies it, and transmits it to the analysis module. The analysis module converts the voltage signal wave into a pressure value and transmits it to the control module. The control module includes a central processing unit and a transmission module connected to it. The central processing unit converts the pressure value into the number of motor rotations and controls the motor through the transmission module to make the pressing head complete the lifting and lowering action. After the lifting and lowering action is completed, the central processing unit receives a new pressure value after 1-2 seconds and continues to operate. The operation is repeated until the received pressure value is consistent with the preset pressure value.

[0006] A further technical solution of the present invention is: the pressing head includes a silicone sleeve connected to the screw and a pressing plate below it. One part of the pressing plate is an arc-shaped hard plate facing the puncture site, and the other part is a soft plate facing the skin opening. The skin contact surface of the soft plate is coated with hemostatic agent. The arc-shaped hard plate has a good pressing effect on the puncture site, and the soft plate has a gentler contact with the skin opening and can stop bleeding in the skin and muscles.

[0007] A further technical solution of the present invention is: absorbent paper is laid on the soft board, and hemostatic agent is sprayed on the surface of the absorbent paper. The absorbent paper can absorb the blood in the muscle and skin from the puncture site to the skin opening, preventing the formation of bruising and blood clots.

[0008] A further technical solution of the present invention is: the analysis module converts the voltage signal wave into a pressure change wave through analysis, and selects the average peak value of the pressure change wave within a 3-5 second time period to obtain the pressure value. Selecting the average peak value within a 3-5 second time period as the pressure value is more consistent with the pulse beat pattern and the reaction speed is also fast enough.

[0009] A further technical solution of the present invention is: the number of motor rotations N = (F1-F0)×K, where F1 is the pressure value output by the analysis module, F0 is the pressure value preset in the central processing unit, and K is the conversion factor. K is determined by the motor speed and the diameter of the transmission shaft, which reduces the variables generated during use to a single variable F1, resulting in low computational pressure and fast response.

[0010] A further technical solution of the present invention is: K = K0 × n × L / t, where n is the rotational speed of the motor, L is the circumference of the transmission shaft of the motor, t is the rotation time of the transmission shaft, and K0 is the physiological medical ratio of the change in puncture site pressure to the change in dorsalis pedis pulse pressure. Using a standard physiological medical ratio for K0 can achieve the best compression hemostasis force most quickly.

[0011] A further technical solution of the present invention is: K = K0 × n × L / t, where n is the rotational speed of the motor, L is the circumference of the transmission shaft of the motor, t is the rotation time of the transmission shaft, and K0 is 1, which can quickly achieve the best pressure hemostasis force after repeated intelligent operation 3 times.

[0012] A further technical solution of the present invention is: the motor is a miniature slow-speed forward and reverse motor. The slow speed facilitates precise control. Forward rotation can compress and stop bleeding, while reverse rotation can relax the pressure on the thigh after the compression and hemostasis have achieved a certain effect.

[0013] A further technical solution of the present invention includes a footboard, which is an arc-shaped plate. The upper surface of the footboard fits against the patient's leg. A ball bearing groove is opened in the lower part of the footboard, and the ball bearing is placed in the ball bearing groove with a portion protruding below the ball bearing groove. A sliding groove is opened on the side of the footboard. A rolling groove is opened on the upper surface of the fixing plate. The upper surface of the rolling groove is a sliding plate that flips inward on both sides. When the sliding plate is slid into the sliding groove along the arc, the ball bearing just touches the upper part of the ball bearing groove and the lower part of the rolling groove. The length of the footboard is greater than the length of the fixing plate. In use, the footboard is first placed under the patient's thigh, and then the fixing plate is installed. Since the puncture point is not directly above the patient's thigh, during the pressing of the pressing head, the pressing head and the fixing plate form a vertical force on the footboard. Under the action of the ball bearing, the fixing plate will slide to the optimal position of the footboard. In this way, the intelligent compression hemostasis device can achieve the most stable placement after femoral artery puncture. The effective compression force is the greatest during the compression hemostasis process and the device is not easy to shake. The friction between the footboard and the patient's thigh is large, which will prevent displacement and improve comfort.

[0014] A further technical solution of the present invention is that the upper surface of the foot plate is covered with a disposable silicone sleeve, which only needs to be replaced each time it is used, which is both hygienic and saves on usage costs.

[0015] The beneficial effects of the present invention are as follows: Due to the adoption of the above technical solution, the intelligent compression hemostasis device after femoral artery puncture of the present invention ensures good blood supply to the lower limbs based on the minimum continuous pulsation force of the dorsalis pedis pulse, and then reverses this premise to obtain the optimal compression hemostasis force, which can achieve the best compression hemostasis effect. Furthermore, during the compression hemostasis process, it is continuously adjusted according to the patient's physical signs to obtain the dynamic optimal compression hemostasis effect. Attached Figure Description

[0016] Figure 1 This is a schematic diagram of the structure of the intelligent compression hemostasis device after femoral artery puncture according to the present invention;

[0017] Figure 2 This is a structural block diagram of an intelligent compression hemostasis device for femoral artery puncture as described in this invention. Detailed Implementation

[0018] The present invention will be further described below with reference to the accompanying drawings and specific embodiments.

[0019] Example:

[0020] like Figure 1 and Figure 2The device shown is an intelligent compression hemostasis device for femoral artery puncture, comprising an inductive pressure transducer. The inductive pressure transducer includes a pair of magnetically conductive housings, each housing containing an inductive coil. An elastic diaphragm is clamped between the two housings. The two inductive coils, together with two non-inductive resistors in a dynamic pressure measuring instrument, form a test bridge. A metal bowl is added to the pressure receiving port of the transducer, with a circular hole at the top communicating with the air gap of the transducer, forming a probe 1 for pulse taking. The two ends of the probe are connected by a steel band 2 to form a wristwatch shape. The probe is then placed on the dorsalis pedis pulse to make contact with the pulse. The steel strap is tightly fastened. When the pulse on the back of the foot beats, it causes a change in the air volume inside the bowl. The gas inside the bowl communicates with the air gap of the inductive pressure transducer, thus causing the diaphragm to shift. The diaphragm's shift in turn converts the air gap change into a voltage change. This minute voltage change generates an electrical signal that enters the signal acquisition module of the intelligent control system 9. After being amplified by the signal acquisition module, it is transmitted to the analysis module. The analysis module converts the electrical signal into a pressure change wave and selects the average peak value of the pressure change wave over a certain period of time (generally 3-5 seconds) to obtain the pressure value F1. The pressure value automatic input control module includes a central processing unit (CPU) and a connected transmission module. The CPU converts the pressure value into the number of motor rotations N. The CPU is preset with the pressure value F0 at which the weakest dorsalis pedis pulse needs to be preserved during compression hemostasis. N = (F1 - F0) × K, where K is the conversion coefficient. The transmission module controls the rotation of a miniature, slow-speed, forward and reverse-rotating motor. The power cylinder 5 is mounted above the threaded sleeve and includes a motor 6. The motor 6 controls the screw 7 to move in and out of the threaded sleeve 8, thus controlling the exposed length of the screw. When N is positive... When N is a numerical value, the motor rotates forward to control the screw to press down. When N is negative, the motor rotates in reverse to control the screw to lift up. When N is 0, it remains stationary. The lower end of the screw is connected to a pressing head, which includes a silicone sleeve connected to the screw and a pressing plate below it. One part of the pressing plate is an arc-shaped hard plate 11 facing the puncture site, and the other part is a soft plate 12 facing the skin opening. The skin contact surface of the soft plate is coated with hemostatic agent. The screw sleeve is connected to an arc-shaped fixing plate 3 located below the pressing head via an arc-shaped connecting rod 4. The fixing plate is connected to the foot plate 10 via ball bearings and slots. The foot plate fits snugly under the patient's thigh. The upper surface of the foot plate is covered with a disposable silicone sleeve.

[0021] The inductive pressure transducer is equipped with switch K1, and the central processing unit is equipped with switch K2. During use, first attach the probe to the dorsalis pedis pulse, ensuring tight contact, and then fasten the steel band. Next, activate switch K1, open the slot sealing plate, insert the arc-shaped fixing plate into the foot plate slot, and close the slot sealing plate. Place the patient's thigh on the foot plate, aligning the pressure head with the puncture site. Then, activate switch K2. The central processing unit automatically adjusts the pressure to achieve optimal hemostasis. During hemostasis, as the hemostasis effect occurs and the patient's blood flow changes, the central processing unit automatically adjusts the pressure based on the dorsalis pedis pulse, solving problems such as the inability to adjust the pressure according to blood flow, leading to bruising, muscle bleeding, and hemostasis failure.

[0022] When no pressure is applied, the diaphragm is positioned between the two housings, with a gap between the diaphragm and the housing δ1 = δ2, coil inductance L1 = L2, and resistance R1 = R2. At this time, the bridge is in equilibrium and has no output signal. If pressure is applied to the transducer diaphragm, the diaphragm shifts, causing one side of the gap between the housing and the diaphragm to increase while the other side decreases. Then δ1 ≠ δ2, and the change is Δδ1 = Δδ2. The magnetic circuit of the inductor coil is a loop formed by the magnetically conductive housing, diaphragm, and air gap. The change in the air gap causes a change in the magnetic reluctance of the magnetic circuit, resulting in a change in inductance, making L1 ≠ L2. This disrupts the bridge's balance, and the bridge output is now ΔV, which is proportional to the applied pressure. Therefore, the change in pulse wave pressure is converted into an electrical charge.

[0023] The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of the present invention should be included within the protection scope of the present invention.

Claims

1. A smart compression hemostasis device after femoral artery puncture, characterized in that: The device includes a dorsalis pedis pulse strength detector, which includes an inductive pressure transducer. The inductive pressure transducer contains a pair of magnetically conductive housings, each housing containing an inductive coil. An elastic diaphragm is sandwiched between the two housings. The two inductive coils and two non-inductive resistors in a dynamic pressure measuring instrument form a test bridge. A metal bowl is added to the pressure receiving port of the inductive pressure transducer. The top of the bowl has a round hole that communicates with the air gap of the transducer, forming a pulse-taking probe. The two ends of the probe are connected with a steel band to form a wristwatch-shaped dorsalis pedis pulse strength detector. It also includes a compression device comprising an arc-shaped fixing plate acting on the lower part of the patient's thigh. The fixing plate is connected to a threaded sleeve acting on the upper part of the patient's thigh via a connecting rod. A power cylinder is installed above the threaded sleeve, and a motor is installed in the power cylinder. The motor drives a screw to move up and down within the threaded sleeve. The lower end of the screw is connected to a pressing head for pressing the puncture site. The pressing head includes a silicone sleeve connected to the screw and a pressing plate below it. One part of the pressing plate is an arc-shaped hard plate facing the puncture site, and the other part is facing the skin. The compression device includes a soft plate with hemostatic agent on its skin contact surface. The foot plate is an arc-shaped plate with its upper surface conforming to the patient's leg. The lower part of the foot plate has a ball bearing groove, in which the ball bearing is placed and partially protrudes. The side of the foot plate has a sliding groove. The upper surface of the fixing plate has a rolling groove, and the upper surface of the rolling groove is a two-sided inward sliding plate. When the sliding plate is slid into the sliding groove along the arc, the ball bearing just touches the upper part of the rolling groove and the lower part of the rolling groove. The length of the foot plate is greater than the length of the fixing plate. It also includes an intelligent control system, which comprises a signal acquisition module, an analysis module, and a control module. The signal acquisition module receives and amplifies the voltage signal wave generated by the test bridge in the dorsalis pedis pulse strength detector and transmits it to the analysis module. The analysis module converts the voltage signal wave into a pressure value and transmits it to the control module. The control module includes a central processing unit and a transmission module connected to it. The central processing unit converts the pressure value into the number of motor rotations and controls the motor through the transmission module to make the pressing head complete the lifting and lowering action. After the lifting and lowering action is completed, the central processing unit receives a new pressure value after 1-2 seconds and continues to operate. The operation is repeated until the received pressure value is consistent with the preset pressure value. A switch K1 is set on the inductive pressure transducer and a switch K2 is set on the central processing unit.

2. The intelligent compression hemostasis device after femoral artery puncture according to claim 1, characterized in that: The flexible board is covered with absorbent paper, and the surface of the absorbent paper is sprayed with hemostatic agent.

3. The intelligent compression hemostasis device after femoral artery puncture according to claim 1, characterized in that: The analysis module converts the voltage signal wave into a pressure change wave by analysis, and selects the average peak value of the pressure change wave over a period of 3-5 seconds to obtain the pressure value.

4. A smart compression hemostasis device after femoral artery puncture according to any one of claims 1-3, characterized in that: The number of motor rotations N = (F1 - F0) × K, where F1 is the pressure value output by the analysis module, F0 is the pressure value preset in the central processing unit, and K is the conversion factor, which is determined by the motor speed and the diameter of the transmission shaft.

5. The intelligent compression hemostasis device after femoral artery puncture according to claim 4, characterized in that: The formula K = K0 × n × L / t is given, where n is the rotational speed of the motor, L is the circumference of the motor's drive shaft, t is the rotation time of the drive shaft, and K0 is the physiological and medical ratio of the change in pressure at the puncture site to the change in pressure of the dorsalis pedis pulse.

6. The intelligent compression hemostasis device after femoral artery puncture according to claim 4, characterized in that: The formula K = K0 × n × L / t is given, where n is the motor speed, L is the circumference of the motor's drive shaft, t is the rotation time of the drive shaft, and K0 is 1.

7. A smart compression hemostasis device after femoral artery puncture according to any one of claims 1-3, characterized in that: The motor is a miniature slow-speed forward and reverse motor.

8. The intelligent compression hemostasis device after femoral artery puncture according to claim 1, characterized in that: The upper surface of the footplate is covered with a disposable silicone sleeve.

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