CN113143444A - Cardiac pulse electric field ablation catheter device - Google Patents

Cardiac pulse electric field ablation catheter device Download PDF

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CN113143444A
CN113143444A CN202110114068.2A CN202110114068A CN113143444A CN 113143444 A CN113143444 A CN 113143444A CN 202110114068 A CN202110114068 A CN 202110114068A CN 113143444 A CN113143444 A CN 113143444A
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pulse
electric field
area
ablation
electrode
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不公告发明人
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Shanghai Xuanyu Medical Equipment Co ltd
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Shanghai Xuanyu Medical Equipment Co ltd
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/1206—Generators therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A61B18/1402—Probes for open surgery
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A61B18/1492—Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00053—Mechanical features of the instrument of device
    • A61B2018/00214—Expandable means emitting energy, e.g. by elements carried thereon
    • A61B2018/0022—Balloons
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00315—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for treatment of particular body parts
    • A61B2018/00345—Vascular system
    • A61B2018/00351—Heart
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
    • A61B2018/00577—Ablation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A61B2018/1405—Electrodes having a specific shape

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Abstract

A cardiac pulse electric field ablation catheter device comprises an operating handle, a bending adjusting assembly, a guide wire channel assembly and an ablation assembly, wherein the ablation assembly comprises a guide wire and a plurality of pulse electrodes, at least one annular area can be formed after the ablation assembly is released, the pulse electrodes are arranged at positions which can be uniformly distributed in the annular area at intervals, an area where the pulse electrodes can generate an electric field is a work applying area, and the work applying area of each pulse electrode is arranged at a position where the annular area is abutted against a target ablation tissue; the pulse electrode is mainly contacted with the target ablation area tissue, and the area of the electrode contacted with the target ablation area is not less than that of the electrode contacted with the non-target ablation area; the pulse electric field generated by the electrodes is mainly acted on the tissues in the target ablation area, but not on non-target ablation areas such as blood and the like, so that the damage to the tissue cells and the related complications are reduced.

Description

Cardiac pulse electric field ablation catheter device
Technical Field
The invention relates to the technical field of tissue ablation equipment, in particular to a cardiac pulsed electric field ablation catheter device.
Background
Atrial fibrillation (atrial fibrillation) is the most common cardiac arrhythmia with an incidence of about 2% and increasing progressively with age. The most serious complication of atrial fibrillation is thromboembolism, which can lead to stroke, myocardial infarction, etc., with stroke being the most common complication of atrial fibrillation death.
There are two broad categories of methods of treating atrial fibrillation, namely drug therapy and non-drug therapy. According to the electrocardio-physiology and pace-making division of the Chinese medical society, the prescription of atrial fibrillation: current understanding and treatment recommendations-2015 "current drug treatment for atrial fibrillation mainly includes: control ventricular rate, restore and maintain sinus rhythm, and antithrombotic therapy. The medical treatment includes anti-arrhythmia treatment and anticoagulation treatment, and the purpose of the anti-arrhythmia treatment is to prevent atrial fibrillation, control fast rate of atrial fibrillation, remove atrial fibrillation and maintain sinus rate. Commonly used drugs include arrhythmia, digoxin, betamethake, and codantone. The anticoagulant therapy aims to prevent the formation of mural thrombus in the atria and prevent other organ column embolism, particularly cerebral embolism, caused by the falling of the mural thrombus in the atria, and the commonly used medicine is warfarin.
The non-drug treatment of atrial fibrillation comprises ablation treatment, surgical treatment, pacing treatment and the like, is suitable for treating patients with poor atrial fibrillation effect or unsuitable for drug treatment by a drug method, and can cure atrial fibrillation by successful ablation treatment and surgical treatment.
Currently, catheter ablation is an effective means for atrial fibrillation patients to restore and maintain sinus rhythm. Catheter ablation is dominated by radio frequency energy, but there are other sources of energy (including cryo-, ultrasound-, and laser ablation, etc.). However, these thermal/cold energy conduction based ablations have certain limitations, lack of selectivity for tissue destruction in the ablation region, and rely on catheter abutment to the ablated tissue, so that damage may occur to the adjacent esophagus, coronary arteries, phrenic nerve, and the like. Certain complications exist in the perioperative period of the operation, and part of patients can relapse due to the catheter sticking effect, the depth of focus and the like. Reportedly, the recurrence rate of radiofrequency ablation is 20-40%, and the recurrence rate of cryoablation is 10-30%;
in recent years, pulsed electric field ablation has begun to be explored for use in the field of cardiac ablation, both at home and abroad, and promising results have been achieved. Unlike conventional energy, pulsed electric field energy forms irreversible micropores in cell membranes by transient discharge, causing apoptosis, achieving the goal of non-thermal ablation, also known as irreversible electroporation. Currently, electroporation ablation has been used as an effective means of destroying malignant tumor tissue. Pulsed electric field ablation can theoretically damage myocardial cells without heating the tissue, and has cell/tissue selectivity, protecting key structures around the ablated tissue.
The principle of pulse ablation is that a short dc high voltage pulse can generate an electric field of several hundred volts in a range of several centimeters, and the electric field can generate damage on cell membranes to form perforations. If the electric field developed at the cell membrane is greater than the threshold, the electroporation formed is irreversible, keeping the stomata open. Resulting in cell necrosis or apoptosis. Thus, pulse ablation is a non-thermal biological ablation, as opposed to radiofrequency, cryotherapy, microwave, ultrasound. Can effectively avoid the damage of blood vessels, nerves and esophagus.
From the existing clinical results and literature reports, the pulse ablation has not solved the problem that the high-voltage electric field is applied to the ablated tissue, and the formed electric field causes electric field interference on peripheral nerves and other cells. Although general anesthesia is given to the patient during the operation, the patient still feels pain. In addition, in the electric field ablation process, different electric field applications need to be carried out on different tissues, and the dynamic adjustment of the electric field energy is also needed for the tissue change in the ablation process. Meanwhile, relevant literature studies show that pulsed electric field ablation results in a significant increase in current density in the blood near the catheter due to the lower electrical resistance of the blood in the ventricular cavity of the heart compared to the myocardial tissue. Electrolysis of blood may result in the generation of microbubbles in the blood. It will likely increase the risk of stroke in the patient.
Therefore, in order to reduce tissue cell damage and reduce related complications, a new ablation catheter product design is needed that can precisely and effectively control the application of a pulsed electric field to targeted myocardial tissue that needs to be ablated.
Disclosure of Invention
Aiming at the defects and shortcomings of the prior art, the cardiac pulsed electric field ablation catheter device is provided, and the main purpose of the cardiac pulsed electric field ablation catheter device is to enable the pulsed electric field generated by the electrodes to mainly act on the tissues in the target ablation area, reduce the damage to the tissue cells and reduce the related complications.
In order to achieve the above object, the present invention provides the following technical solutions.
The utility model provides a heart pulse electric field melts pipe device, includes operating handle, transfers curved subassembly, seal wire channel subassembly and melts the subassembly, melt the subassembly and include the wire and connect in a plurality of pulse electrode of wire, melt the subassembly and can form the subassembly that melts of at least one annular region after the release, pulse electrode set up in but even interval distribution in the position of annular region, the region that pulse electrode can produce the electric field is the acting region, each pulse electrode's acting region set up in the position that the target of contradicting in annular region melts the tissue.
In one embodiment, the ablation assembly comprises at least one conducting wire, each conducting wire is bent to form a circular ring after being released, the conducting wires are coaxially arranged, the conducting wires are tubular and are uniformly loaded with the pulse electrodes at intervals, each ring segment of each conducting wire, which is used for loading the pulse electrodes, is a loading area, the pulse electrodes are distributed at intervals along the axial direction of the conducting wires, and the working area of each pulse electrode is smaller than the surface area of the loading area.
In one embodiment, the wires are co-planar and co-axial after release.
In one embodiment, the loops formed by each of the leads after release are disposed in different planes, and the diameter of the loop formed by the lead is not greater than the diameter of the loop formed by the adjacent lead from the distal end to the proximal end.
In one embodiment, the pulse electrode is in a semicircular ring shape and is attached to and loaded on the surface of the lead, and the radian of the pulse electrode is less than 2 pi.
In one embodiment, the pulse electrode is annularly sleeved on the surface of the lead, the pulse electrode comprises the working area and the non-working area, the surface of the non-working area of the pulse electrode is covered with the insulating layer, and the area of the working area is smaller than that of the non-working area.
In one embodiment, the pulse electrodes are arranged on the surface of the lead in a dot-like protruding manner.
In one embodiment, the loading area is sleeved with a circular reinforcing tube, and the pulse electrode is convexly arranged on the surface of the reinforcing tube.
In one embodiment, the ablation assembly comprises an insulating balloon and a plurality of conducting wires, wherein the pulse electrodes are sheet-shaped pulse electrodes and are arranged at positions which are uniformly distributed in a circle at intervals along the surface of the balloon after the balloon is released.
In one embodiment, the number of the pulse electrodes in the loop is not less than two, and the number of the pulse electrodes distributed in each loop is not less than 2.
Compared with the prior art, the invention has the beneficial effects that: the ablation assembly is a pulse electrode for transmitting a pulse electric field, and is mainly contacted with target ablation area tissues, and the area of the electrode contacted with the target ablation tissues is not less than that of the electrode contacted with a non-target ablation area; the pulse electric field generated by the electrodes is mainly acted on the tissues in the target ablation area, but not on non-target ablation areas such as blood and the like, so that the damage to the tissue cells and the related complications are reduced.
Drawings
FIG. 1 is a schematic diagram of an ablation assembly of a cardiac pulsed electric field ablation catheter device in one embodiment;
FIG. 2 is a schematic view of an ablation assembly of a cardiac pulsed electric field ablation catheter apparatus in another embodiment;
FIG. 3 is a schematic view of an ablation assembly of a cardiac pulsed electric field ablation catheter apparatus in yet another embodiment;
FIG. 4 is a schematic diagram of a pulse electrode structure of a cardiac pulsed electric field ablation catheter apparatus in one embodiment;
FIG. 5 is a schematic diagram of a pulse electrode structure of a cardiac pulsed electric field ablation catheter device in another embodiment;
fig. 6 is a schematic diagram of a pulse electrode structure of a cardiac pulsed electric field ablation catheter device in yet another embodiment.
Detailed Description
The technical solution of the present invention is further explained in detail with reference to the drawings and the embodiments.
As shown in fig. 1, 2 or 3, a cardiac pulse electric field ablation catheter device includes an operating handle, a bending component, a guide wire channel component and an ablation component, where the ablation component includes a lead 10 and a plurality of pulse electrodes 20 connected to the lead 10, the ablation component is an ablation component that can form at least one annular region after release, the pulse electrodes 20 are disposed at positions that can be uniformly distributed in the annular region at intervals, a region where the pulse electrodes 20 can generate an electric field is a work-applying region, and the work-applying region of each pulse electrode is disposed at a position where the annular region butts against a target ablation tissue. Wherein the release is defined as the process of the ablation assembly entering the working state after the vascular puncture.
The ablation assembly is a pulse electrode 20 used for transmitting a pulse electric field, and is mainly contacted with the tissue of a target ablation area, and the area of the electrode contacted with the target ablation tissue is not less than that of the electrode contacted with the non-target ablation area; the pulse electric field generated by the electrodes is mainly acted on the tissues in the target ablation area, but not on non-target ablation areas such as blood and the like, so that the damage to the tissue cells and the related complications are reduced.
As shown in fig. 1, in one embodiment, the ablation assembly includes at least one conducting wire 10, each conducting wire 10 is bent to form a circular ring, the conducting wires 10 are coaxially arranged, the conducting wires 10 are tubular and used for loading pulse electrodes 20, and a circular ring section of each pulse electrode 20 is a loading area; a plurality of the pulse electrodes 20 are distributed at intervals along the axial direction of the lead 10, and the working area of each pulse electrode 20 is smaller than the surface area of the loading area.
In this embodiment, the rings formed by each of the leads 10 are disposed on different planes, and from the distal end to the proximal end, the diameter of the ring formed by the lead 10 is not greater than the diameter of the ring formed by the adjacent lead 10. Wherein, the near end and the far end define the distance between the described object and the operator in the process of the catheter operation, for example, the near end refers to the end of the catheter closer to the operator, namely the end closer to the blood vessel puncture site. The far end is the end of the catheter far away from the operator, namely the end far away from the blood vessel puncture position.
In one embodiment as shown in fig. 2, the wires 10 are disposed co-planarly and coaxially.
As shown in fig. 4, in one embodiment, the pulse electrode 20a is in a shape of a half-circle ring and is attached to and loaded on the surface of the lead 10, and the radian of the pulse electrode 20a is smaller than 2 pi. In this manner, the missing arc portion of the pulse electrode 20a can be made to not contact the target ablation tissue, while the remaining arc portion of the electrode can be made to contact the target ablation tissue. The pulse electrode 20a may be a semi-annular electrode or a crescent-shaped electrode.
As shown in fig. 5, in another embodiment, the pulse electrode 20b is annularly sleeved on the surface of the lead 10, the pulse electrode 20b includes the working area and the non-working area, the pulse electrode 20b is covered with the insulating layer 21 on the surface of the non-working area, and the area of the working area is smaller than that of the non-working area.
That is, in the present embodiment, by subjecting a part of the surface of the ring-shaped pulse electrode 20b to insulation treatment so that the insulated part of the pulse electrode 20b does not contact the target ablation tissue and the non-insulated part of the pulse electrode 20b contacts the target ablation tissue, the area of the pulse electrode 20b where the pulse electrode 20b contacts the tissue to be ablated is not lower than the area of the pulse electrode 20b which contacts blood. Such as by coating, painting, etc., a layer of insulating material is added to the pulse electrode 20b where it is desired to insulate. There are various ways to insulate the pulse electrode 20b, including but not limited to coating with a layer of a biocompatible insulating material, such as polyester, phenolic resin, melamine resin, epoxy resin, polyimide resin, silicone, organic fluorine resin, ceramic, etc.
In yet another embodiment, as shown in fig. 6, the pulse electrode 20c is disposed on the surface of the lead 10 in a dot-like protruding manner.
In one embodiment, the loading area is covered with a circular reinforcing tube 30, and the pulse electrode 20c is protruded on the surface of the reinforcing tube 30.
That is, in this embodiment, the shape of the pulse electrode 20c may be a point-like or convex electrode, so that the pulse electrode 20c is in contact with only the target ablation tissue, and in order to improve the bonding strength between the pulse electrode 20c and the lead wire 10, a reinforcing tube 30 may be filled between the lead wire 10 and the pulse electrode 20c, so that the bonding between the lead wire 10 and the electrode is more firm.
As shown in fig. 3, in one embodiment, the ablation assembly includes an insulating balloon 30 and a plurality of conducting wires 10, and the pulse electrodes 20 are sheet-like pulse electrodes disposed at positions evenly spaced and looped along the surface of the balloon 30 after the balloon 30 is released.
In this embodiment, the ablation assembly is formed by a balloon 30 and a plurality of pulse electrodes 20, and the pulse electrodes 20 may be configured as sheet electrodes, flexible electrodes, or the like. One side of the pulse electrode 20 is in contact with the target ablation tissue, such as the pulmonary venous vestibulum, and the other side is in contact with the surface of the balloon 30. The balloon 30 used in the present invention may be made of polymer material with insulating property, such as Pebax, PA, TPU, etc., and the electric field generated by the pulse electrode 20 is mainly transmitted in the target ablation tissue and is not transmitted in the balloon 30.
Further, the number of the pulse electrodes 20 on the balloon 30 is not less than 4, and the arrangement of the pulse electrodes 20 on the surface of the balloon 3054 is not less than two circles, and the number of the pulse electrodes 20 in each circle is not less than 2. The number of the pulse electrodes 20 may be defined as the number of times the pulse electrodes 20 are arranged to form one turn in the circumferential direction of the surface of the balloon 30. Specifically, each circle of pulse electrodes 20 should be uniformly distributed on the circumferential surface of the balloon 30, and the number of pulse electrodes 20 per circle is preferably 3-6. And selecting corresponding balloon 30 wing number for folding according to the number of the pulse electrodes 20 per circle, wherein the wing number of the balloon 30 folding is equal to the number of the pulse electrodes 20 per circle. If the number of the pulse electrodes 20 per circle is 3, the balloon 30 is folded in three wings; if the number of pulse electrodes 20 per circle is 6, the balloon 30 is folded in six wings, so that the pulse electrodes 20 can be uniformly distributed on the surface of the balloon 30 after the balloon 30 is expanded.
Furthermore, the corresponding electric field ablation parameters can be selected for ablation according to the distance between the pulse electrodes 20 on the surface of the balloon 30. Considering that the circumferential distance between the pulse electrodes 20 on the surface of the balloon 30 (i.e., the circumferential distance between the pulse electrodes 203 and 206 shown in fig. 3) is further increased with the expansion of the balloon 30, it may be designed to adjust the parameters of the electric field ablation according to the compliance of the expansion of the balloon 30 so as to maintain the intensity of the pulse electric field emitted by the pulse electrodes 20 on the surface of the balloon 30 not to be significantly reduced with the expansion of the balloon 30, and in particular, to gradually increase the voltage of the pulse electric field ablation as the pressure of the expansion of the balloon 30 is increased and the circumferential distance between the pulse electrodes 20 on the surface of the balloon 30 is increased.
Furthermore, the electric field direction of the electric field ablation can be adjusted according to the distribution of the pulse electrodes 20 on the surface of the balloon 30; to achieve different directions of ablation of the electric field, such as circumferentially along the pulmonary vein (e.g., the pulse electrode 203 and the pulse electrode 206 form a pair of electric fields as shown in fig. 3), axially along the pulmonary vein (e.g., the pulse electrode 202 and the pulse electrode 203 form a pair of electric fields), and angularly with respect to the axial direction of the pulmonary vein (e.g., the pulse electrode 202 and the pulse electrode 206 form a pair of electric fields). Different ablation directions help to increase the probability that the cell membrane is electroporated in multiple directions; since electroporation occurs most easily in the radial direction of the cell membrane, which coincides with the direction of the electric field.
Furthermore, the ablation parameters can be formed according to the specification of the balloon 30 and correspond to the specification of the balloon 30. Specifically, the distance between the two pulse electrodes 20 forming the electric field on the surface of the balloon 30 is proportional to the amplitude of the pulse voltage applied to the two pulse electrodes 20, that is, when the distance between the pulse electrodes 20 forming the electric field changes, the amplitude of the pulse voltage forming the electric field correspondingly changes. So that the pulse voltage amplitude per unit distance is maintained approximately horizontal.
The above description is only a preferred embodiment of the present invention, and all equivalent changes or modifications of the structure, characteristics and principles described in the present invention are included in the scope of the present invention.

Claims (10)

1. The utility model provides a heart pulse electric field melts pipe device, includes operating handle, transfers curved subassembly, seal wire channel subassembly and melts the subassembly, its characterized in that, it includes the wire and connects in a plurality of pulse electrode of wire to melt the subassembly, melts the subassembly and can form the subassembly that melts of at least one annular region after releasing, pulse electrode set up in can even interval distribution in annular region's position, the region that pulse electrode can produce the electric field is the acting region, each pulse electrode's acting region set up in annular region conflicts the position that the target melts the tissue.
2. The cardiac pulsed electric field ablation catheter device of claim 1, comprising: the ablation assembly comprises at least one conducting wire, each conducting wire is bent to form a circular ring after being released, the conducting wires are coaxially arranged, the conducting wires are tubular and are evenly loaded with the pulse electrodes at intervals, each ring segment of each conducting wire, which is used for loading the pulse electrodes, is a loading area, the pulse electrodes are distributed at intervals along the axial direction of the conducting wires, and the working area of each pulse electrode is smaller than the surface area of the loading area.
3. The cardiac pulsed electric field ablation catheter device of claim 2, wherein the wires are co-planar and co-axial after delivery.
4. The cardiac pulsed electric field ablation catheter device of claim 2, wherein the loops formed by each of the wires after release are disposed in different planes and have a diameter from the distal end to the proximal end that is no greater than the diameter of the loops formed by adjacent wires.
5. The cardiac pulsed electric field ablation catheter device as set forth in any one of claims 2 to 4, wherein: the pulse electrode is in a semicircular ring shape and is attached to and loaded on the surface of the lead, and the radian of the pulse electrode is smaller than 2 pi.
6. The cardiac pulsed electric field ablation catheter device as set forth in any one of claims 2 to 4, wherein: the pulse electrode is sleeved on the surface of the lead in a circular ring shape, the pulse electrode comprises a working area and a non-working area, an insulating layer is covered on the surface of the non-working area of the pulse electrode, and the area of the working area is smaller than that of the non-working area.
7. The cardiac pulsed electric field ablation catheter device as set forth in any one of claims 2 to 4, wherein: the pulse electrode is arranged on the surface of the lead in a dot-shaped protruding mode.
8. The cardiac pulsed electric field ablation catheter device of claim 7, wherein: the loading region is sleeved with a circular reinforcing tube, and the pulse electrode is convexly arranged on the surface of the reinforcing tube.
9. The cardiac pulsed electric field ablation catheter device of claim 1, wherein: the ablation assembly comprises an insulating balloon and a plurality of conducting wires, and the pulse electrodes are sheet-shaped pulse electrodes and are arranged at positions where the sheet-shaped pulse electrodes are evenly distributed at intervals to form a circle on the surface of the balloon after the balloon is released.
10. The cardiac pulsed electric field ablation catheter device of claim 9, wherein: the number of the pulse electrodes in a loop is not less than two, and each loop of the pulse electrodes is not less than 2.
CN202110114068.2A 2021-01-28 2021-01-28 Cardiac pulse electric field ablation catheter device Pending CN113143444A (en)

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Cited By (3)

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CN113662654A (en) * 2021-09-13 2021-11-19 杭州旸瑞医疗器械有限公司 Ablation device and ablation catheter thereof
CN113729923A (en) * 2021-09-30 2021-12-03 上海睿刀医疗科技有限公司 Surface ablation electrode catheter and ablation equipment
WO2023125647A1 (en) * 2021-12-31 2023-07-06 深圳市先健呼吸科技有限公司 Ablation apparatus

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CN113662654B (en) * 2021-09-13 2022-01-11 杭州旸瑞医疗器械有限公司 Ablation device and ablation catheter thereof
CN113729923A (en) * 2021-09-30 2021-12-03 上海睿刀医疗科技有限公司 Surface ablation electrode catheter and ablation equipment
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