A coronary myocardial bridge pulsed field ablation catheter system

Abstract

This invention belongs to the field of medical device technology, and specifically relates to a pulsed field ablation catheter system for coronary artery myocardial bridging. It includes a pulsed electric field ablation structure and a disposable pulsed electric field ablation catheter. A connecting wire is located on the back side of the pulsed electric field ablation structure, and the other end of the connecting wire is movably engaged with the disposable pulsed electric field ablation catheter. By using the disposable pulsed electric field ablation catheter, the catheter body drives an inflatable balloon through the arterial tube to reach the myocardial bridging lesion. The contrast fluid injected into the external tube gradually expands the balloon, causing it to unfold and allowing the electrode pads to adhere to the vessel wall for pulsed electric field ablation. This eliminates the need for the strong adhesion required by traditional thermal or cold ablation, effectively avoiding vascular damage caused by excessive local energy, and providing an efficient and reliable solution for the clinical treatment of coronary artery myocardial bridging.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to a coronary artery myocardial bridge pulse field ablation catheter system. Background Technology

[0002] Myocardial bridging refers to a segment of a coronary artery that runs within the myocardium, covered by myocardial fibers, forming a bridge-like structure. This covered segment of the vessel is called the myocardial coronary artery. Normally, coronary arteries should reside within the fatty tissue beneath the epicardium. The presence of myocardial bridging causes this segment of the vessel to be compressed during cardiac systole, potentially leading to hemodynamic abnormalities, myocardial ischemia, and inducing arrhythmias, myocardial depression, left ventricular dysfunction, syncope, or even sudden death.

[0003] Currently, catheter ablation primarily utilizes the thermal effect of radiofrequency energy and the cold effect of cryotherapy. These ablation methods lack selectivity in destroying tissue in the ablation area and rely heavily on catheter adhesion. The ablation procedures are lengthy, and therefore, within the thermal zone, there is a risk of damage to adjacent structures such as the esophagus, phrenic nerve, and blood vessels. In certain locations, interference from cardiac pulsation and respiratory movements can occur; poor catheter adhesion can lead to incomplete pulmonary vein isolation and recurrence of atrial fibrillation.

[0004] Therefore, we propose a coronary artery myocardial bridge pulse field ablation catheter system to solve the above problems. Summary of the Invention

[0005] To address the shortcomings of existing technologies, this invention provides a coronary artery myocardial bridge pulse field ablation catheter system, which solves the problems mentioned in the background section.

[0006] To achieve the above objectives, the present invention specifically adopts the following technical solution: A coronary artery myocardial bridge pulse field ablation catheter system includes a pulse field ablation structure and a disposable pulse field ablation catheter. A connecting wire is provided on the back side of the pulse field ablation structure, and the other end of the connecting wire is movably snapped into the disposable pulse field ablation catheter. The disposable pulsed electric field ablation catheter includes a holding sleeve, an inner tube body is fixedly inserted into the inner side of the holding sleeve, a tee tube is fixedly installed at the input end of the inner tube body, an access tube is fixedly installed at the top end of the tee tube, and a connecting connector is fixedly sleeved at the output end of the inner tube body.

[0007] Furthermore, the pulsed electric field ablation structure includes a movable base, the bottom of which is provided with four self-locking casters, and the top of which is fixedly mounted with a pulsed electric field ablation instrument. A mounting bracket is movably engaged with the notch of the pulsed electric field ablation instrument.

[0008] Furthermore, a connecting back frame is fixedly installed at the top of the mounting bracket, and a touch screen is movably snapped onto the front side of the connecting back frame. A power supply connector and a control switch are provided on the surface of the mounting bracket, and the pulse electric field ablation instrument is electrically connected to the touch screen, the power supply connector, and the control switch.

[0009] Furthermore, a placement platform is fixedly fitted onto the surface of the mounting bracket, and a push-pull handle is provided on the surface of the placement platform. A hanging frame is fixedly installed on the side wall of the mounting bracket, and the connecting wires are wrapped around the hanging frame when not in use.

[0010] Furthermore, the connecting wire includes a protective sleeve, and an embedded tube is provided inside the protective sleeve, and an electrode wire is provided inside the embedded tube.

[0011] Furthermore, the protective sleeve is an epoxy resin-filled hollow tube, and the inner tube body is a polytetrafluoroethylene coated tube.

[0012] Furthermore, the input end of the access pipe is movably connected to a closing pin and an injection valve, the input port of the injection valve is movably connected to two external pipes, and the output end of the access pipe is fixedly connected to a mating joint.

[0013] Furthermore, the other end of the mating joint is movably connected to a connecting pipe, the other end of the connecting pipe is connected to the interior of the socket joint, the output end of the socket joint is fixedly connected to a hollow tube, and the other end of the hollow tube is movably connected to a conduit body.

[0014] Furthermore, a sleeve is movably fitted at the connection between the socket joint and the hollow tube, and a reinforcing sleeve is provided at the connection between the sleeve and the socket joint.

[0015] Furthermore, an inflatable balloon is provided on the surface of the catheter body, and four electrode pads are provided on the surface of the inflatable balloon, with the four electrode pads arranged symmetrically at equal intervals.

[0016] Compared with the prior art, the present invention provides a coronary artery myocardial bridge pulse field ablation catheter system, which has the following beneficial effects: This invention utilizes a disposable pulsed electric field ablation catheter. The catheter body carries an expandable balloon through the arterial tube to the myocardial bridging lesion. The contrast fluid injected into the external tube gradually expands the balloon, causing the electrode pads to adhere to the blood vessel wall for pulsed electric field ablation. This eliminates the need for the strong adhesion required by traditional thermal or cold ablation, effectively avoiding vascular damage caused by excessive local energy. This provides an efficient and reliable solution for the clinical treatment of coronary artery myocardial bridging. Attached Figure Description

[0017] Figure 1This is a schematic diagram of the structure of the present invention; Figure 2 This is a schematic diagram of the pulsed electric field ablation structure of the present invention; Figure 3 This is a schematic diagram of the connecting wires of the present invention; Figure 4 This is a schematic diagram of the closed state of the disposable pulsed electric field ablation catheter of the present invention; Figure 5 This is a schematic diagram of the injection state of the disposable pulsed electric field ablation catheter of the present invention; Figure 6 This is a schematic diagram of the inner tube body of the present invention; Figure 7 This is a schematic diagram of the inflatable balloon of the present invention.

[0018] In the diagram: 1. Pulsed electric field ablation structure; 101. Movable base; 102. Pulsed electric field ablation instrument; 103. Mounting bracket; 104. Connecting back frame; 105. Touch screen; 106. Power connector; 107. Placement platform; 108. Hanging frame; 109. Control switch; 2. Connecting wires; 201. Protective sleeve; 202. Inner tube body; 203. Electrode wires; 3. Disposable pulsed electric field ablation catheter; 301. Holding sleeve; 302. Inner tube body; 303. T-connector; 304. Access tube; 305. Closing pin; 306. Injection valve; 307. Outer tube; 308. Socket connector; 309. Connecting tube; 310. Butt connector; 311. Sleeve; 312. Reinforcing sleeve; 313. Hollow tube; 314. Catheter body; 315. Inflatable balloon; 316. Electrode pads. Detailed Implementation

[0019] The technical solutions of 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. Example

[0020] like Figures 1-7 As shown, an embodiment of the present invention provides a coronary artery myocardial bridge pulse field ablation catheter system, including a pulse electric field ablation structure 1 and a disposable pulse electric field ablation catheter 3. A connecting wire 2 is provided on the back side of the pulse electric field ablation structure 1, and the other end of the connecting wire 2 is movably connected to the disposable pulse electric field ablation catheter 3.

[0021] The disposable pulsed electric field ablation catheter 3 includes a holding sleeve 301, an inner tube body 302 is fixedly inserted into the inner side of the holding sleeve 301, a three-way tube 303 is fixedly installed at the input end of the inner tube body 302, an access tube 304 is fixedly installed at the top end of the three-way tube 303, and a connecting connector 308 is fixedly sleeved at the output end of the inner tube body 302.

[0022] like Figure 2 As shown, in some embodiments, the pulsed electric field ablation structure 1 includes a movable base 101, the bottom of which is provided with four self-locking casters, and the top of which is fixedly mounted with a pulsed electric field ablation instrument 102. A mounting bracket 103 is movably engaged with the notch of the pulsed electric field ablation instrument 102.

[0023] Specifically, the self-locking casters at the bottom of the mobile base 101 enable flexible movement and fixation of the equipment, facilitating position adjustment within the operating room according to operational needs.

[0024] The mounting bracket 103, which is movably snapped into the notch of the pulse electric field ablation instrument 102, provides a stable mounting base for other components, which facilitates the integration and assembly of components and is also beneficial for later maintenance and replacement.

[0025] like Figure 2 As shown, in some embodiments, a connecting back frame 104 is fixedly installed on the top of the mounting bracket 103, and a touch screen 105 is movably snapped onto the front side of the connecting back frame 104. A power supply connector 106 and a control switch 109 are provided on the surface of the mounting bracket 103. The pulse electric field ablation instrument 102 is electrically connected to the touch screen 105, the power supply connector 106, and the control switch 109.

[0026] Specifically, the pulse electric field ablation instrument 102 outputs a high-voltage, short-pulse waveform with an output voltage of 500V to 2000V and a pulse width of 0.1us to 50us. The pulse energy is released within the absolute refractory period of the cardiac cycle.

[0027] The pulsed electric field ablation instrument 102 has the function of detecting R-waves, and generally releases pulse energy about 50ms to 200ms after the R-wave is detected.

[0028] The core mechanism of pulsed electric field ablation lies in causing irreversible electroporation by breaking down the myocardial cell membrane through a high-voltage electric field.

[0029] 1. Microscopic Effects of Electrical Pulses: High-intensity (1800-2000 volts), extremely short-duration (nanosecond to microsecond) electric field pulses applied to cardiomyocytes can momentarily disrupt the homeostasis of ions inside and outside the cell, leading to the formation of nanoscale pores (electroporation) in the cell membrane lipid bilayer. Low-energy, short-duration pulses may only create temporary (reversible) pores; however, when the pulse intensity and number reach a threshold, irreversible hydrophilic pores will form in the cell membrane, increasing cell membrane permeability, disrupting the normal ion gradient inside and outside the cell, and causing programmed apoptosis in the affected cardiomyocytes.

[0030] 2. Selective tissue ablation: The myocardial cell membrane has a critical electric field threshold significantly lower than that of surrounding tissues (myocardial cells: 300-400 V / cm; esophageal smooth muscle cells: 1600 V / cm; nerve cells: 3800 V / cm). Therefore, a pulsed electric field with specific parameters can effectively ablate diseased myocardial cells while minimizing damage to adjacent important structures such as coronary arteries. This is the theoretical basis for the most important advantage of pulsed electric field ablation.

[0031] 3. Non-thermal ablation mechanism: Although the energy generated by pulsed electric field ablation can be partially converted into heat energy, its discharge duration is extremely short. The dominant effect is electroporation of myocardial cell membranes. Therefore, the tissue temperature only rises slightly, which significantly reduces the risk of overheating that cannot be completely avoided by traditional radiofrequency ablation: when the temperature exceeds 100°C, steam bursting (cardiac tamponade) and blood carbonization (shedding and causing thrombosis) will occur.

[0032] The connecting back frame 104 at the top of the mounting bracket 103 is connected to the front movable card of the control screen 105. Medical staff can intuitively set ablation parameters and monitor various data during the ablation process, such as pulse voltage, frequency, and duration, through the control screen 105, thus realizing convenient human-computer interaction.

[0033] The power supply connector 106 on the surface of the mounting bracket 103 is used to connect to an external power source to supply power to the entire pulse electric field ablation structure 1, while the control switch 109 can quickly realize the start and stop control of the equipment to ensure the safety of operation.

[0034] The electrical connection between the pulse electric field ablation instrument 102 and the touch screen 105, power supply connector 106 and control switch 109 ensures stable signal and power transmission between the components, enabling the system to work in coordination.

[0035] like Figure 2 As shown, in some embodiments, a placement platform 107 is fixedly sleeved on the surface of the mounting bracket 103, and a push-pull handle is provided on the surface of the placement platform 107. A hanging frame 108 is fixedly installed on the side wall of the mounting bracket 103, and the connecting wire 2 is wound around the hanging frame 108 when idle.

[0036] Specifically, the surface space of the placement table 107 can be used to temporarily place small tools or consumables needed during the operation, improving the convenience of the operation.

[0037] The push-pull handle is ergonomically designed, making it easy for medical staff to adjust the position of the mounting bracket 103 according to the surgical position, thus reducing the burden of operation.

[0038] The mounting bracket 108 effectively solves the storage problem of the connecting wire 2. When not in use, the connecting wire 2 can be wrapped around the mounting bracket 108 on the side wall, avoiding the risk of tripping due to the wire falling or the equipment wiring becoming messy, keeping the operating environment clean and orderly, ensuring the safety and standardization of the surgical environment, and also providing a certain degree of protection for the connecting wire 2 and extending its service life.

[0039] like Figure 3 As shown, in some embodiments, the connecting wire 2 includes a protective sleeve 201, an embedded tube 202 is provided inside the protective sleeve 201, and an electrode wire 203 is provided inside the embedded tube 202.

[0040] Specifically, the protective sleeve 201 provides effective physical protection for the internal embedded tube 202 and electrode wire 203, which can isolate external mechanical damage, liquid corrosion and electromagnetic interference, and ensure that the connecting wire 2 maintains structural stability and reliable performance in complex surgical environments.

[0041] The embedded tube 202 serves as a receiving channel for the electrode wires 203, which helps to maintain the regular arrangement of the electrode wires 203, avoids the wires from getting tangled or squeezed together, and ensures the stability of signal transmission.

[0042] The electrode wire 203 serves as the transmission medium for pulsed electric field energy and control signals. It can efficiently transmit the pulsed energy generated by the pulsed electric field ablation instrument 102 to the electrode plate 316 of the disposable pulsed electric field ablation catheter 3. At the same time, it can also transmit the feedback signal from the catheter end back to the instrument in a timely manner, thereby achieving precise control and monitoring of the ablation process.

[0043] like Figure 3 As shown, in some embodiments, the protective sleeve 201 is an epoxy resin-filled hollow tube, and the inner tube body 202 is a polytetrafluoroethylene coated tube.

[0044] Specifically, epoxy resin-filled hollow tubes, used as protective sleeves 201, have excellent bonding strength and mechanical properties, effectively enhancing overall rigidity and resistance to deformation. When the tube is subjected to external impact or internal pressure changes, it can reduce the degree of deformation of the tube and protect the internal structure from damage.

[0045] As an embedded tube body 202, the polytetrafluoroethylene coated tube has extremely low surface energy and chemical inertness, making it difficult for corrosive substances to react chemically with it, thus reducing corrosion and pollution to the tube body.

[0046] like Figure 6 As shown, in some embodiments, the input end of the access pipe 304 is movably connected to a closing pin 305 and an injection valve 306, the input port of the injection valve 306 is movably connected to two external pipes 307, and the output end of the access pipe 304 is fixedly connected to a mating joint 310.

[0047] Specifically, the closing pin 305 and the injection valve 306 are used alternately. When it is necessary to inject contrast fluid, the closing pin 305 is pulled out and the injection valve 306 is inserted. The contrast fluid is injected into the access tube 304 through the external tube 307. When injection is not required, pull out the injection valve 306 and insert the closing pin 305 to ensure the sealing of the conduit system when not in use.

[0048] The two external tubing units 307 allow for the separate or combined injection of different types of contrast fluids, meeting diverse clinical operational needs.

[0049] First, based on the local diameter of the target blood vessel and the specific expansion pressure parameters of the 315 balloon, a suitable working pressure value needs to be determined. It is generally recommended to set it in the range of 6 to 8 atmospheres (atm).

[0050] Subsequently, the balloon 315 was slowly and steadily inflated using a mixture of contrast agent and saline solution in appropriate proportions, so that it could fully conform to the inner wall of the blood vessel.

[0051] After the balloon is inflated and reaches the preset pressure, the appropriate ablation energy parameters are selected according to the actual treatment needs, that is, the electric field strength is set to 1000 to 2000 volts per centimeter (V / cm). Under these conditions, the device is started to carry out precise and controllable ablation treatment.

[0052] like Figure 7 As shown, in some embodiments, the other end of the mating joint 310 is movably connected to a connecting pipe 309, the other end of the connecting pipe 309 is connected to the interior of the socket joint 308, the output end of the socket joint 308 is fixedly connected to a hollow pipe 313, and the other end of the hollow pipe 313 is movably connected to a conduit body 314.

[0053] Specifically, the connector 310 provides a robust connection structure between the access tube 304 and subsequent connecting components, ensuring that the contrast fluid can smoothly pass through the access tube 304 into the subsequent transmission path.

[0054] The connecting tube 309 serves as a channel connecting the butt joint 310 and the socket joint 308. Its material selection takes into account both flexibility and pressure resistance. It can bend appropriately as the catheter body 314 moves in the blood vessel, and it can withstand the pressure when the contrast fluid is injected, thus avoiding leakage of contrast fluid due to tube rupture.

[0055] The hollow tube 313 connects the connecting sleeve 308 and the catheter body 314. The internal hollow structure provides a path for the contrast fluid to flow to the inflatable balloon 315. At the same time, its outer material has a certain degree of support, which can prevent the catheter body 314 from being excessively bent during the push process and blocking the contrast fluid channel.

[0056] The 314-inch diameter of the catheter body conforms to the anatomical features of the coronary artery. Its smooth surface reduces frictional damage to the inner wall of the vessel. The gradually narrowing tip facilitates passage through tortuous vessels to reach the lesion site. Furthermore, it exhibits good radiolucency under X-ray fluoroscopy, allowing the operator to monitor the catheter's position and direction in real time.

[0057] Hollow tube 313 is generally made of medical polymer materials with good flexibility, softness and elasticity, such as Pebax (nylon) and PU (polyurethane), while the catheter body 314 is made of polymer materials with good lubricity, such as PTFE (polytetrafluoroethylene) and HDPE (high-density polyethylene).

[0058] The effective length of the disposable pulsed electric field ablation catheter 3 is the length of the catheter body 314. The effective length is the part that can enter the human blood vessels, and the effective length is generally more than 50cm.

[0059] like Figure 7 As shown, in some embodiments, a sleeve 311 is movably sleeved at the connection between the socket joint 308 and the hollow tube 313, and a reinforcing sleeve 312 is provided at the connection between the sleeve 311 and the socket joint 308.

[0060] Specifically, the sleeve 311 is used to wrap and fix the connection between the sleeve joint 308 and the hollow tube 313, which enhances the structural stability of the connection and prevents the connection from loosening or breaking due to concentrated force during the pushing or pulling of the conduit.

[0061] The reinforcing sleeve 312 further fills the gap between the sleeve 311 and the connecting joint 308, increasing the contact area and friction to enhance the overall connection strength, ensuring that the contrast fluid will not leak from the connection gap during transmission, thus guaranteeing the safety and smoothness of the surgical procedure.

[0062] like Figure 7As shown, in some embodiments, the surface of the catheter body 314 is provided with an inflatable balloon 315, and the surface of the inflatable balloon 315 is provided with four electrode pads 316, which are symmetrically arranged at equal intervals.

[0063] Specifically, the inflatable balloon 315 is an inflatable balloon with a maximum diameter of 2.5~3.0mm. The inflatable diameter can be adjusted according to the pressure to ensure that after inflation, the electrode pad 316 is close to the blood vessel wall and tightly attached to the covered myocardial bundle. It can be adjusted on the imaging before inflation to ensure stable position and close contact.

[0064] Electrode 316 features a single-sided flexible dual-electrode design, with one positive and one negative electrode, concentrating the electric field on the myocardial bridge on the outer side of the blood vessel wall, reducing electrical stimulation towards the heart. It also reduces the difficulty of catheter manufacturing, ensuring the catheter is sufficiently thin and flexible, minimizing stimulation and damage to the coronary arteries.

[0065] The surface of the inflatable balloon 315 near the electrode plate 316 is coated with an insulating material. The insulating material can be PTPE (polytetrafluoroethylene) coating, pyrene coating, PI (polyimide) coating, etc., to ensure that the inflatable balloon 315 and the electrode plate 316 are always in an insulating state.

[0066] After the contrast fluid enters the expandable balloon 315 through the above-mentioned path, the balloon will gradually expand according to the increase of the injected volume. Since the four electrode pads 316 are symmetrically arranged at equal intervals on the surface of the balloon, the uniform expansion of the balloon can ensure that each electrode pad 316 forms a stable and uniform contact with the blood vessel wall, thereby ensuring the uniformity of the pulse electric field distribution in the lesion area and improving the consistency and reliability of the ablation effect.

[0067] When used, percutaneous coronary angiography is used to determine the location of myocardial bridges and assess their stenosis and compression during diastole and systole while the patient is under general anesthesia. Administer medication systemically or intracoronaryly to the patient to reduce vasospasm. Replace the working sheath with the target vessel, allowing the guidewire to enter the distal end of the vessel. Using the OTW guidewire, insert the catheter body 314 and the inflatable balloon 315 into the artery through the guidewire, and gradually and slowly push the inflatable balloon 315 to the myocardial bridging lesion. Based on the local blood vessel diameter, select an appropriate pressure to expand the balloon 315, with a pressure range of 6-8 atm. Use a mixture of contrast agent and normal saline to inflate the balloon 315. Under angiography, the situation is confirmed again to ensure that the electrode pair is reliably and closely attached to the vessel wall where the myocardial bridge is located.

[0068] At this point, imaging, pacing, and / or impedance testing can be used to help determine whether the electrode pair is accurately oriented towards the myocardial bridge. Select an appropriate ablation energy, within the range of 1000-2000 V / cm, and activate the pulsed electric field ablation instrument 102 to begin ablation treatment. After the ablation procedure is completed, the fluid in the balloon is withdrawn, and the condition of the blood vessels and the patient is assessed. Angiography is used to determine the condition of the blood vessels after ablation, the compression of the myocardial bridge, and the patient's vital signs. The observation period is then waited to ensure safety. After the procedure, the OTW guidewire and sheath were removed, the skin wound was treated, and the procedure was completed. Once the patient had recovered from anesthesia, cardiac and blood pressure monitoring was initiated.

[0069] In summary, by setting up a disposable pulsed electric field ablation catheter 3, the catheter body 314 carries the expandable balloon 315 through the arterial tube to reach the myocardial bridging lesion. The contrast fluid injected in the external tube 307 gradually expands the expandable balloon 315, causing the electrode pad 316 to adhere to the blood vessel wall for pulsed electric field ablation. This eliminates the need for the strong adhesion required by traditional thermal or cold ablation, effectively avoiding vascular damage caused by excessive local energy. This provides an efficient and reliable solution for the clinical treatment of coronary artery myocardial bridging.

[0070] It should be noted that the specific models and specifications of the pulse electric field ablation instrument 102, touch screen 105, control switch 109, electrode wire 203, and electrode plate 316 in the coronary artery myocardial bridge pulse field ablation catheter system need to be selected and determined according to the actual specifications of the device. The specific selection calculation method adopts the existing technology in this field, so it will not be described in detail.

[0071] Furthermore, the power supply and operating principle of the pulse electric field ablation instrument 102, touch screen 105, control switch 109, electrode wire 203, and electrode sheet 316 in the coronary artery myocardial bridge pulse field ablation catheter system are clear to those skilled in the art and will not be described in detail here.

[0072] Furthermore, the working principles and wiring methods of the pulse electric field ablation instrument 102, touch screen 105, control switch 109, electrode wire 203, and electrode plate 316 in the coronary artery myocardial bridge pulse field ablation catheter system are commonplace and belong to conventional methods or common knowledge. They will not be elaborated here. Those skilled in the art can make any selections according to their needs or convenience.

[0073] In the idle areas of this device, all the aforementioned electrical components, which refer to power elements, electrical components, and compatible controllers and power supplies, are connected by wires. The electrical connections between the various electrical components are completed in the order of their operation. The detailed connection methods are well-known technologies in this field.

[0074] It should be noted that parts have a lifespan and can be replaced during regular maintenance when they no longer meet performance requirements. Deterioration in performance due to prolonged use of parts is not a design defect of this application.

[0075] Finally, it should be noted that the above descriptions are merely preferred embodiments of the present invention and are not intended to limit the present invention. Although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art can still modify the technical solutions described in the foregoing embodiments or make equivalent substitutions for some of the technical features. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the protection scope of the present invention.

Claims

1. A coronary artery myocardial bridge pulsed field ablation catheter system, comprising a pulsed electric field ablation structure (1) and a disposable pulsed electric field ablation catheter (3), characterized in that: The back side of the pulse electric field ablation structure (1) is provided with a connecting wire (2), and the other end of the connecting wire (2) is movably connected to the disposable pulse electric field ablation catheter (3). The disposable pulsed electric field ablation catheter (3) includes a holding sleeve (301), an inner tube body (302) is fixedly inserted into the inner side of the holding sleeve (301), a three-way tube (303) is fixedly installed at the input end of the inner tube body (302), an access tube (304) is fixedly installed at the top end of the three-way tube (303), and a connecting connector (308) is fixedly sleeved at the output end of the inner tube body (302).

2. The coronary artery myocardial bridge pulsed field ablation catheter system according to claim 1, characterized in that: The pulsed electric field ablation structure (1) includes a movable base (101), the bottom of which is provided with four self-locking casters, and the top of which is fixedly installed with a pulsed electric field ablation instrument (102). The recess of the pulsed electric field ablation instrument (102) is movably engaged with a mounting bracket (103).

3. The coronary artery myocardial bridge pulsed field ablation catheter system according to claim 2, characterized in that: The top of the mounting bracket (103) is fixedly mounted with a connecting back frame (104), and the front side of the connecting back frame (104) is movably connected to a touch screen (105). The surface of the mounting bracket (103) is provided with a power supply connector (106) and a control switch (109). The pulse electric field ablation instrument (102) is electrically connected to the touch screen (105), the power supply connector (106), and the control switch (109).

4. The coronary artery myocardial bridge pulsed field ablation catheter system according to claim 2, characterized in that: The mounting bracket (103) is fixedly fitted with a placement platform (107), and the surface of the placement platform (107) is provided with a push-pull handle. The side wall of the mounting bracket (103) is fixedly installed with a hanging frame (108), and the connecting wire (2) in the idle state is wrapped with the hanging frame (108).

5. The coronary artery myocardial bridge pulsed field ablation catheter system according to claim 1, characterized in that: The connecting wire (2) includes a protective sleeve (201), and an embedded tube (202) is provided inside the protective sleeve (201). An electrode wire (203) is provided inside the embedded tube (202).

6. The coronary artery myocardial bridge pulsed field ablation catheter system according to claim 5, characterized in that: The protective sleeve (201) is an epoxy resin-filled hollow tube, and the inner tube body (202) is a polytetrafluoroethylene coated tube.

7. The coronary artery myocardial bridge pulsed field ablation catheter system according to claim 1, characterized in that: The input end of the access pipe (304) is movably connected to a closing pin (305) and an injection valve (306). The input port of the injection valve (306) is movably connected to two external pipes (307). The output end of the access pipe (304) is fixedly connected to a mating joint (310).

8. The coronary artery myocardial bridge pulsed field ablation catheter system according to claim 7, characterized in that: The other end of the docking joint (310) is movably connected to a connecting pipe (309), the other end of the connecting pipe (309) is connected to the inside of the socket joint (308), the output end of the socket joint (308) is fixedly connected to a hollow pipe (313), and the other end of the hollow pipe (313) is movably connected to a conduit body (314).

9. A coronary artery myocardial bridge pulsed field ablation catheter system according to claim 8, characterized in that: A sleeve (311) is movably sleeved at the connection between the socket joint (308) and the hollow tube (313), and a reinforcing sleeve (312) is provided at the connection between the sleeve (311) and the socket joint (308).

10. A coronary artery myocardial bridge pulsed field ablation catheter system according to claim 8, characterized in that: The surface of the catheter body (314) is provided with an inflatable balloon (315), and the surface of the inflatable balloon (315) is provided with four electrode pads (316), which are symmetrically arranged at equal intervals.

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