CN216495608U - Pulsed electric field balloon component and ablation catheter device applying same - Google Patents

Abstract

The utility model discloses a pulsed electric field balloon component and an ablation catheter device using the same. The pulsed electric field balloon component comprises a balloon and can be inflated and deformed; the first electrodes are uniformly distributed on the surface of the saccule and are positioned on the far end surface of the saccule; the second electrodes are uniformly distributed on the surface of the balloon, and the second electrodes are positioned on the middle surface of the balloon; the first electrode and the second electrode are configured for pulse ablation, and the first electrode and the second electrode are deformed along with the deformation of the balloon. An ablation catheter device comprises the pulsed electric field balloon component and a catheter component. Set up first electrode on the distal end surface of sacculus, set up the second electrode at the middle part face of sacculus, the sacculus is inflated after filling, and the distance between the electrode keeps getting very stable, utilizes mutually supporting between the electric field that first electrode, second electrode formed to carry out the pulse ablation to this homogeneity and the stability of ablating of guaranteeing pulse electric field distribution.

Description

Pulsed electric field balloon component and ablation catheter device applying same

Technical Field

The utility model relates to the technical field of medical equipment, in particular to a pulsed electric field balloon component and an ablation catheter device using the same.

Background

Irreversible electroporation (IRE) is a rapidly developing and FDA-approved treatment for solid tumors. IRE may be a promising approach for cardiac Ablation, especially in comparison to RF, where it can produce lesions without thermal injury related complications, i.e. the ability to preserve surrounding tissue structure, such high voltage pulses are more commonly referred to in the art as Pulsed Electric Field Ablation (PFA).

The use of PFA for the treatment of Atrial Fibrillation (AF) has been the focus of recent research in the field of arrhythmia. PFA ablation catheters are often designed in a basket shape with a plurality of splines, each spline having a plurality of ablation electrodes thereon. The purpose of such a design is to hopefully obtain a ring-like lesion for the purpose of rapid isolation of the pulmonary veins.

The ablative effect of a pulsed electric field depends on the electric field strength between the electrodes. Due to the structure of the basket-shaped conduit, the distance between the splines cannot be kept uniform and constant when certain external force is applied. If the ablation between the splines is attempted on the basket catheter, the output energy is constant, and as a result, the electric field intensity between the splines at a longer distance is smaller, and the electric field intensity between the splines at a shorter distance is larger. In extreme cases, if the splines are held together under external forces, short circuits or arcing may result.

The utility model relates to a balloon-shaped pulsed electric field ablation catheter, which is used for improving the ablation effect of the device in the treatment of Atrial Fibrillation (AF).

SUMMERY OF THE UTILITY MODEL

According to one aspect of the present invention, there is provided a pulsed electric field balloon member comprising

The balloon can be pressurized to deform and comprises a distal end surface and a middle surface;

the first electrodes are uniformly distributed on the far end surface of the saccule;

the second electrodes are uniformly distributed on the middle surface of the balloon;

the first electrodes and the second electrodes can deform along with the deformation of the balloon, and the distances between the first electrodes and/or the distances between the second electrodes are equal after the balloon is inflated.

The utility model discloses a balloon component special for emitting a pulse electric field. Among this sacculus component, set up first electrode on the distal end surface of sacculus, set up the second electrode at the middle part face of sacculus, the sacculus is inflated after filling, and the distance between the electrode keeps getting very stable, and pulsed electric field is provided to first electrode, and pulsed electric field is provided to the second electrode, utilizes mutually supporting between the electric field that first electrode, second electrode formed to carry out the pulse ablation, can enlarge the adaptability that the pulsed electric field ablated to different size pulmonary vein oral area, improves and melts the effect, improves and melts stability.

In some embodiments, the pulsed electric field balloon member further comprises a plurality of splines corresponding to the second electrodes in number, the splines are uniformly distributed on the inner wall of the balloon cavity of the balloon, and the splines are respectively connected with the corresponding second electrodes; a portion of the splines are connected to the first electrode.

Thus, the splines provide a qualitative support for the balloon, and the splines also provide energy to the electrodes, enabling them to deliver a pulsed electric field.

In some embodiments, the pulsed electric field balloon member further comprises a plurality of third electrodes circumferentially arrayed on the surface of the balloon, the plurality of third electrodes being located on the distal end face of the balloon and spaced apart from the plurality of first electrodes.

Thus, the third electrode is a functional electrode, which may be a mapping, identification, or the like; the functional integrity of the component is improved.

In some embodiments, a portion of the splines are connected to third electrodes, and any two third electrodes cooperate to record an electrocardiogram signal in the heart chamber.

Therefore, the third electrode is set as a functional electrode for recording electrocardiogram signals in the heart cavity, is mainly used for identifying whether the pulmonary veins are isolated or not, and is more beneficial to the treatment of Atrial Fibrillation (AF).

In some embodiments, the first electrode has a trapezoidal shape, and the distal end of the first electrode has a short side; after the balloon is inflated, the adjacent oblique edges of the two adjacent first electrodes are parallel.

Therefore, the first electrode at the far end of the sacculus is approximately in a trapezoidal shape, the far end is a short side and conforms to the cambered surface of the far end face of the sacculus, and the electrodes are always approximately parallel in the process of radiating outwards from the center of the sacculus so as to ensure the distribution uniformity of the pulse electric field.

In some embodiments, the first electrode is triangular in shape with the proximal end of the electrode being the base; after the balloon is inflated, the adjacent oblique edges of the two adjacent first electrodes are parallel to each other.

Therefore, the first electrodes positioned at the far end of the balloon are approximately triangular, the bottom edges of the first electrodes are positioned at the near end and conform to the cambered surface of the far end surface of the balloon, and the first electrodes are always approximately parallel in the process of radiating outwards from the center of the balloon, so that the uniformity of pulse electric field distribution is ensured.

In some embodiments, the second electrode is rectangular; the edges of two adjacent second electrodes are parallel to each other.

Therefore, the second electrodes positioned on the middle surface of the balloon are approximately rectangular and conform to the cambered surface of the middle surface of the balloon, and the second electrodes are always approximately parallel to each other in the process of radiating outwards from the center of the balloon, so that the ablation stability of the pulsed electric field is ensured.

In some embodiments, the cooperation between any two first electrodes can record electrocardiogram signals in the heart cavity;

or any two second electrodes are matched with each other to record electrocardiogram signals in the heart cavity;

or the electrocardiogram signals in the heart cavity can be recorded by matching any one of the first electrodes with any one of the second electrodes.

Therefore, by the requirement, the electrocardiogram signals in the heart cavity can be recorded in a matching way.

In some embodiments, the ablation catheter device comprises the pulsed electric field balloon member and a catheter component, wherein the catheter component is provided with a pressure transmission cavity, and the balloon is arranged at the distal end of the catheter component and is communicated with the pressure transmission cavity;

the catheter component comprises a first catheter and a second catheter, the second catheter is sleeved outside the first catheter, a balloon body of the balloon is connected with the far end of the second catheter, and the far end of the first catheter penetrates through a balloon cavity of the balloon and is connected with the far end of the balloon; the pressure transmission cavity is formed between the first conduit and the second conduit.

Therefore, the pressure transmission cavity between the second catheter and the first catheter is communicated with the balloon, and the balloon can be expanded by injecting pressure into the proximal ends of the second catheter and the first catheter; the near end of the balloon is connected with the second catheter, and the far end of the balloon is connected with the first catheter, so that the balloon is stably fixed.

In some embodiments, the catheter assembly further comprises a third catheter, the third catheter is sleeved outside the second catheter, a conductive cavity is formed between the third catheter and the second catheter, and a plurality of conductive wires are arranged in the conductive cavity corresponding to the plurality of splines;

the plurality of conductive wires are respectively connected with the plurality of splines.

Therefore, the balloon catheter is further provided with a third catheter, a conductive cavity is formed between the third catheter and the second catheter, a conductive wire can be installed, the spline poles on the inner wall of the balloon cavity are powered, and therefore the electrodes on the surface of the balloon are powered.

The utility model has the following beneficial effects: the balloon is expanded or contracted by pressure, the spline on the inner wall of the balloon cavity of the balloon is opened after the balloon is expanded, the electrode on the surface of the balloon is unfolded, and the uniform distance between the spline and the electrode can be ensured after the balloon is expanded, so that the uniformity of electric field distribution is improved; in addition, the adjacent edges of the expanded electrodes are parallel, so that the uniformity of pulse electric field distribution can be improved. Moreover, the electrodes are arranged on the far end surface and the middle surface of the balloon, the electric field formed by the two groups of electrodes is wide in range, the balloon can adapt to pulmonary vein mouths with different sizes, and the ablation effect can be improved. This makes the device more beneficial in the treatment of atrial fibrillation.

Drawings

Fig. 1 is a schematic perspective view of an inflated, expanded ablation catheter device in accordance with an embodiment of the present invention.

Fig. 2 is a schematic perspective view of the ablation catheter device of fig. 1 after deflation.

Fig. 3 is a schematic cross-sectional view of the ablation catheter apparatus of fig. 1.

Fig. 4 is an enlarged schematic view of a portion a in fig. 3.

Fig. 5 is an enlarged schematic view of a portion B in fig. 3.

Fig. 6 is an enlarged schematic view of a portion C in fig. 3.

Fig. 7 is a front view of the ablation catheter device of fig. 1.

Fig. 8 is a schematic elevational view of another embodiment of an ablation catheter device in accordance with the utility model after inflation.

Reference numbers in the figures: 100-catheter assembly, 101-pressure delivery lumen, 102-delivery lumen, 103-conducting lumen, 110-first catheter, 120-second catheter, 130-third catheter, 200-balloon, 210-balloon lumen, 220-balloon, 201-medial face, 202-distal face, 300-first electrode, 400-second electrode, 500-spline, 600-third electrode, 700-conducting wire, 800-guide wire, 900-guide head.

Detailed Description

The present invention will be described in further detail with reference to the accompanying drawings.

Example one

Fig. 1-2 schematically illustrate an ablation catheter device according to an embodiment of the present invention, having a proximal end and a distal end, comprising a pulsed electric field balloon member, a catheter assembly 100, the catheter assembly 100 being provided with an infusion pressure lumen 101, the pulsed electric field balloon member being provided at the distal end of the catheter assembly 100 and being in communication with the infusion pressure lumen 101; the pulse electric field balloon component is pressed and expanded, and pulse discharge can be carried out, so that lesion tissues are ablated.

The catheter body is of elongate tubular construction and the proximal portion of the catheter assembly 100 is connected to an operating handle through which the device is controlled.

In this embodiment, to better explain the components in this embodiment, the extending direction of the catheter assembly 100 is designated as the L-axis, and the device is distal when entering the human body first, and proximal when not. With reference to fig. 1-2, the forward direction of the L-axis is designated as the forward-side direction, and the reverse direction is the rearward-side direction. The present device is further described in detail below with reference to the concept of the L-axis.

With reference to fig. 1-3, the pulsed electric field balloon member is composed as follows:

a balloon 200 provided with a balloon 220 and a balloon cavity 210, wherein the balloon 220 can be expanded by filling pressure in the balloon cavity 210, and the balloon 200 is arranged at the distal end of the catheter assembly 100, is communicated with the pressure transmission cavity 101 of the catheter assembly 100 and can be fully or partially expanded; the balloon 200 is constructed of a flexible, compliant material, which may be elastic or inelastic, so long as the balloon 200 expands and expands outwardly under internal forces and contracts when the forces are absent or removed; providing an internal pressure by introducing an inflation medium into the lumen 210 of the inner balloon 200;

a plurality of first electrodes 300 uniformly distributed on the surface of the balloon 200, the plurality of first electrodes 300 being located on the distal end surface 202 of the balloon 200, the first electrodes 300 being configured for pulsed electric field ablation;

a plurality of second electrodes 400 uniformly distributed on the surface of the balloon 200, the plurality of second electrodes 400 being located on the middle surface 201 of the balloon 200, the second electrodes 400 being configured for pulse ablation,

the first and second electrodes 300 and 400 can be deformed according to the deformation of the balloon 200.

In this sacculus 200 component, set up first electrode 300 on the distal end surface of sacculus 200, set up second electrode 400 at the middle part face 201 of sacculus 200, the sacculus 200 is inflated back, the distance between the electrode keeps very stable, pulse electric field is provided to first electrode 300, pulse electric field is provided to second electrode 400, utilize mutually supporting between the electric field that first electrode 300, second electrode 400 formed to carry out the pulse ablation, can enlarge the adaptability of pulse electric field ablation to different size pulmonary vein oral areas, improve and ablate the effect, improve and ablate stability.

As for the inflated shape of the balloon 200, the shape of the balloon 200 is preferably a columnar shape having both circular arc surfaces, and the columnar balloon 200 having both circular arc surfaces is more advantageous for the treatment of Atrial Fibrillation (AF). The balloon 200 is columnar, the proximal end and the distal end of the balloon 200 are both arc surfaces, and the arc surfaces are generally half of the sphere; in the inflated state of the balloon 200, the second electrode 400 can exhibit a side-parallel relationship at the cylindrical surface. By the specific shape of the balloon 200, the electrodes are deformed after the balloon 200 is inflated, and the shape of the electric field formed by the electrodes can be better used for ablation. Therefore, it can be considered that the outer wall surface of the columnar portion of the balloon 200 is the middle surface 201 of the balloon 200 of the present disclosure, and the arc surface at the distal end is the distal end surface 202 of the balloon 200 of the present disclosure.

With reference to fig. 1-3 and 5, the pulsed electric field balloon member further includes a plurality of splines 500 corresponding to the number of the second electrodes 400, the splines 500 are circumferentially arranged on the inner wall of the balloon cavity 210 of the balloon 200, the splines 500 extend in the L-axis direction from the proximal end to the distal end, a portion of the splines 500 are connected to the first electrodes 300, and the splines 500 are respectively connected to the corresponding second electrodes 400. Splines 500 provide a qualitative support for balloon 200, and splines 500 may also provide energy to the electrodes to enable them to deliver a pulsed electric field.

In this embodiment, the spline 500 is made of a flexible circuit board and is embedded in the inner wall of the balloon cavity 210 of the balloon 200, and the spline 500 can also deform along with the deformation of the balloon 200.

With reference to fig. 1-3 and 7, the pulsed electric field balloon member further includes a plurality of third electrodes 600, the third electrodes 600 being circumferentially arrayed on the surface of the balloon 200, the plurality of third electrodes 600 being located on the distal end surface 202 of the balloon 200, the plurality of third electrodes 600 being spaced apart from the plurality of first electrodes 300. The third electrode 600 is a functional electrode, which may be a mapping, identification, etc.; the functional integrity of the component is improved.

With reference to fig. 1-3 and 7, a portion of the spline 500 is connected to the third electrodes 600, and any two third electrodes 600 are matched to record an electrocardiogram signal in the heart chamber, so as to determine whether the pulmonary veins are isolated. The third electrode 600 is preferably configured as a functional electrode for recording electrocardiogram signals in the heart chamber, and is more advantageous for the treatment of Atrial Fibrillation (AF).

With reference to fig. 1-4 and 7, in this embodiment, the first electrode 300, the second electrode 400, and the third electrode 600 are all embedded on the surface of the balloon 220 of the balloon 200, and the plurality of first electrodes 300, the plurality of second electrodes 400, and the plurality of third electrodes 600 are all distributed in an L-axis circumferential array. The first electrode 300, the second electrode 400, and the third electrode 600 are formed in a sheet shape, and are formed of a ductile and flexible metal, such as gold, silver, or the like. Furthermore, in combination with fig. 5 and 7, in an actual production process, in order to avoid the first electrode 300 and the second electrode 400 on the same spline 500 from contacting during the ablation process, the shortest arc length S of the first electrode 300 and the second electrode 400 extending along the surface of the balloon 200 should be set to be 3MM or more, and in this embodiment, in order to reduce the volume of the balloon 200 member, the shortest arc length S of the first electrode 300 and the second electrode 400 extending along the surface of the balloon 200 is set to be 3MM, so that the volume of the balloon 200 member can be minimized, and the first electrode 300 and the second electrode 400 on the same spline 500 can be prevented from contacting to cause a short circuit fault.

It should be noted that the number of the second electrodes 400 is the same as the number of the splines 500, so that each second electrode 400 is electrically connected with the spline 500 through the balloon 220 of the balloon 200; the number of the first electrodes 300 is half of that of the second electrodes 400, so that the first electrodes 300 are electrically connected with a portion of the splines 500; the third electrode 600 can be disposed to be half of the second electrode 400, and the third electrode 600 and the first electrode 300 are distributed in a staggered manner, so that the first electrode 300 is electrically connected to another portion of the spline 500.

In this embodiment, twelve second electrodes 400 are provided, six first electrodes 300 are provided, and six pairs of third electrodes 600 are provided, i.e., twelve in total.

Referring to fig. 7, the first electrode 300 is triangular, specifically, isosceles triangular; the edges and corners of the triangle are in arc transition, and the proximal edge line of the first electrode 300 is the bottom edge; after the balloon 200 is inflated, the adjacent oblique sides of the two adjacent first electrodes 300 are parallel to each other. The first electrode 300 at the distal end of the balloon 200 is substantially triangular, and the bottom edge thereof is located at the proximal end and conforms to the arc surface of the distal end surface 202 of the balloon 200, so that the electrodes are always substantially parallel in the process of radiating from the center of the balloon 200 to the outside, thereby ensuring the uniformity of pulse electric field distribution and improving the ablation stability.

Referring to fig. 7, the second electrode 400 is rectangular, the second electrode 400 extending distally on the medial side 201 of the balloon 200; the edges and corners are in arc transition, and the sidelines of the near end and the far end of the second electrode 400 are short edges; the edges of two adjacent second electrodes 400 are parallel to each other. The second electrodes 400 on the middle surface of the balloon 200 are substantially rectangular and not only conform to the arc surface of the middle surface of the balloon 200, but also are designed to be substantially parallel to each other all the time in the process of radiating outwards from the center of the balloon 200, so that the ablation stability of the pulsed electric field is ensured.

In particular, in conjunction with fig. 1 and 5, the distal portion of the second electrode 400 may be configured to extend into the distal face 202, which may expand the discharge range of the second electrode 400.

With reference to fig. 1 and 7, any two first electrodes 300 are matched with each other to record electrocardiogram signals in the heart cavity; or, the electrocardiogram signals in the heart cavity can be recorded by matching any two second electrodes 400; or, the electrocardiogram signals in the heart cavity can be recorded by the cooperation of any one of the first electrodes 300 and any one of the second electrodes 400. By requirement, the electrocardiogram signals in the heart cavity can be recorded in a matching way as described above. In actual operation, the configuration may be performed by a signal recording system.

In this embodiment, the first electrode 300 and the second electrode 400 are mainly used for forming a pulse electric field to ablate focal tissues, so the areas of the first electrode 300 and the second electrode 400 are relatively large; while the third electrode 600 is mainly used for recording electrocardiogram signals in the heart cavity, particularly signals in pulmonary veins, and the mapping accuracy can be improved by designing the electrocardiogram signals into a smaller surface area and a smaller polar distance.

Referring to fig. 3-4, the catheter assembly 100 includes a first catheter 110 and a second catheter 120, the second catheter 120 is sleeved outside the first catheter 110, a balloon 220 of the balloon 200 is connected to a distal end of the second catheter 120, and a distal end of the first catheter 110 passes through a balloon cavity 210 of the balloon 200 and is connected to a distal end of the balloon 200; the pressure transmission cavity 101 is formed between the first conduit 110 and the second conduit 120. The pressure transmission cavity 101 between the second catheter 120 and the first catheter 110 is communicated with the balloon 200, and pressure is injected at the proximal ends of the second catheter 120 and the first catheter 110, so that the balloon 200 can be inflated; the proximal end of the balloon 200 is connected to the second catheter 120, and the distal end of the balloon 200 is connected to the first catheter 110, thereby stably fixing the balloon 200.

With reference to fig. 3-4, the catheter assembly 100 further includes a third catheter 130, the third catheter 130 is sleeved outside the second catheter 120, a conductive cavity 103 is formed between the third catheter 130 and the second catheter 120, and a plurality of conductive wires 700 are disposed in the conductive cavity 103 corresponding to the plurality of splines 500; a plurality of conductive wires 700 are connected with the plurality of splines 500, respectively. The conductive wire 700 may be provided integrally with the spline 500 or separately, and the arrangement of the conductive wire 700 is not critical to the present disclosure. The conductive cavity 103 formed between the third catheter 130 and the second catheter 120 can be provided with a conductive wire 700 for supplying power to the spline 500 pole on the inner wall of the cavity 210 of the balloon 200, so as to supply power to the electrode on the surface of the balloon 200.

Referring to fig. 3-4, the catheter assembly 100 of this embodiment is described in detail, the catheter assembly 100 includes a first catheter 110, a second catheter 120, and a third catheter 130, the first catheter 110, the second catheter 120, and the third catheter 130 are coaxially disposed and all extend along the L-axis, and the first catheter 110, the second catheter 120, and the third catheter 130 are flexible, i.e., bendable. The first catheter 110, the second catheter 120, the third catheter 130 are all constructed of polyurethane or PEBAX (polyether block amide), and the third catheter 130 on the outermost surface side is further provided with an embedded braided mesh of stainless steel or the like to increase torsional rigidity of the catheter assembly 100 itself, so that when the control handle is rotated, the distal end of the catheter assembly 100 itself will rotate in a corresponding manner.

Referring to fig. 3 to 4, a portion of the distal end of the first catheter 110 protrudes from the lumen of the second conduit, the proximal end of the balloon 220 of the balloon 200 is clamped to the distal ends of the third catheter 130 and the second catheter 120, and the proximal end of the balloon 220 of the balloon 200 is welded to the second catheter 120 and the third catheter 130. The distal end of the first catheter 110 passes through the lumen 210 of the balloon 200 and is connected to the distal end of the balloon 200, the proximal end of the balloon 200 is connected to the second catheter 120, and the distal end of the balloon 200 is connected to the first catheter 110, thereby stably fixing the balloon 200. The pressure transmission cavity 101 between the second catheter 120 and the first catheter 110 is communicated with the balloon 200, and pressure is injected at the proximal ends of the second catheter 120 and the first catheter 110, so that the balloon 200 can be inflated; typically, a solution medium is used to infuse the balloon 200 from the pressure-delivery lumen 101 between the first catheter 110 and the second catheter 120, thereby inflating the balloon 200, such as saline solution, contrast agent, and the like.

In this embodiment, the wall thicknesses of the first catheter 110, the second catheter 120, the third catheter 130, and the balloon 200 are approximately as follows, and the wall thicknesses of the first catheter 110 and the second catheter 120 are 0.10 mm; the third guide tube 130 is used for supporting, and the wall thickness is set to be 0.20 mm; the balloon 200 wall thickness may be set between 0.05-0.10 mm. However, the above description is not essential to the present disclosure, and is merely an example of the present embodiment.

Referring to fig. 3-4, the first catheter 110 has a delivery lumen 102, the delivery lumen 102 can deliver a guide wire 800, and the delivery lumen 102 can deliver various fluids, such as saline, besides the guide wire 800. The first catheter 110 is hollow and defines a delivery lumen 102, and a guidewire 800 can be delivered from the delivery lumen 102.

Referring to fig. 3, the balloon 200-shaped pulsed electric field ablation device further includes a guide head 900, the guide head 900 is sleeved on the distal end of the first catheter 110, the guide head 900 is connected to the distal end of the balloon 200, and the guide head 900 fixes the balloon 200. In this embodiment, the guide head 900 is configured to be flat and round, and the flat and round guide head 900 is more beneficial for guiding the device into the lesion tissue, and is beneficial for treating Atrial Fibrillation (AF). The flat round guide head 900 is safer, and the flat round guide head 900 can reduce the pressure on the endocardium and avoid bursting the heart.

Example two

The second embodiment is substantially the same as the first embodiment, and the difference is the shape structure of the first electrode 300, which is as follows:

referring to fig. 7, the first electrode 300 has a trapezoid shape, specifically, an isosceles trapezoid shape; the edge of the trapezoid is in arc transition, and the far end of the first electrode 300 is the short side of the isosceles trapezoid; after the balloon 200 is inflated, the adjacent oblique sides of the two adjacent first electrodes 300 are parallel. The first electrode 300 at the far end of the balloon 200 is roughly trapezoidal, and the far end is a short side, which not only conforms to the arc surface of the far end surface 202 of the balloon 200, but also keeps roughly parallel during the process of radiating from the center of the balloon 200 to the outside, so as to ensure the uniformity of pulse electric field distribution and the stability of ablation.

EXAMPLE III

The third embodiment is substantially the same as the first embodiment or the second embodiment, and differs from the first embodiment in the implementation of recording the electrocardiogram signals in the heart chamber, specifically as follows:

referring to fig. 7 or 8, the number of the third electrodes 600 may be equal to the number of the second electrodes 400, and then a plurality of the third electrodes 600 are grouped into two, and each group of the third electrodes 600 is inserted between two adjacent first electrodes 300, so that they are distributed in a staggered manner, that is, two third electrodes 600 are disposed on one spline 500. The cooperation between two third electrodes 600 on the same spline 500 can record electrocardiogram signals in the heart cavity.

The balloon 200 is expanded or contracted by pressure, after the balloon 200 is expanded, the spline 500 on the inner wall of the balloon cavity 210 of the balloon 200 is also opened, the electrode on the surface of the balloon 200 is also unfolded, and the uniform distance between the spline 500 and the electrode can be ensured after the balloon 200 is expanded, so that the uniformity of electric field distribution is improved; and the adjacent sides of the expanded electrodes are parallel, so that the uniformity of pulse electric field distribution can be improved. Moreover, the electrodes are arranged on the far end face 202 and the near end face of the balloon 200, and the electric field formed by the two groups of electrodes is wide in range, so that the electrode can adapt to pulmonary vein mouths with different sizes, and the ablation effect can be improved. This makes the device more beneficial in the treatment of atrial fibrillation.

What has been described above are merely some embodiments of the present invention. It will be apparent to those skilled in the art that various changes and modifications can be made without departing from the inventive concept thereof, and these changes and modifications can be made without departing from the spirit and scope of the utility model.

Claims (10)

1. A pulsed electric field balloon member, characterized by comprising

A balloon (200) capable of being inflated to deform and comprising a distal surface (202) and a middle surface (201);

a number of first electrodes (300) uniformly distributed on a distal end surface (202) of the balloon (200);

a plurality of second electrodes (400) which are uniformly distributed on the middle surface (201) of the balloon (200);

the first electrode (300) and the second electrode (400) can be deformed along with the deformation of the balloon (200).

2. The pulsed electric field balloon member according to claim 1, further comprising a plurality of splines (500) corresponding to the number of the second electrodes (400), wherein the splines (500) are uniformly distributed on the inner wall of the balloon cavity (210) of the balloon (200), and the splines (500) are respectively connected with the corresponding second electrodes (400); a portion of the splines (500) are connected to the first electrode (300).

3. The pulsed electric field balloon member according to claim 2, further comprising a number of third electrodes (600), the third electrodes (600) being circumferentially arrayed on the distal end face (202) of the balloon (200) and spaced apart from the first electrodes (300).

4. The pulsed electric field balloon member according to claim 3, wherein a portion of the splines (500) are connected with the third electrode (600); any two third electrodes (600) are matched with each other to record electrocardiogram signals in the heart cavity.

5. The pulsed electric field balloon member of claim 1, wherein any two of the first electrodes (300) cooperate to record an electrocardiogram signal within a heart chamber;

or, the second electrodes (400) are matched with each other to record electrocardiogram signals in the heart cavity;

or, the cooperation between any one of the first electrodes (300) and any one of the second electrodes (400) can record electrocardiogram signals in the heart cavity.

6. The pulsed electric field balloon member according to any one of claims 1-5, wherein the first electrode (300) has a trapezoidal shape, and the distal end of the first electrode (300) has a short side; after the balloon (200) is inflated, the adjacent oblique edges of the two adjacent first electrodes (300) are parallel to each other.

7. The pulsed electric field balloon member according to any one of claims 1-5, wherein the first electrode (300) is triangular; after the balloon (200) is inflated, the adjacent oblique edges of the two adjacent first electrodes (300) are parallel to each other.

8. The pulsed electric field balloon member according to any one of claims 1-5, wherein the second electrode (400) is rectangular; the edges of two adjacent second electrodes (400) are parallel to each other.

9. An ablation catheter device comprising the pulsed electric field balloon member according to any one of claims 2 to 8, further comprising a catheter assembly (100), wherein the catheter assembly (100) is provided with a pressure delivery cavity (101), and the balloon (200) is arranged at the distal end of the catheter assembly (100) and is communicated with the pressure delivery cavity (101);

the catheter assembly (100) comprises a first catheter (110) and a second catheter (120), wherein the second catheter (120) is sleeved outside the first catheter (110), a balloon (220) of the balloon (200) is connected with the distal end of the second catheter (120), and the distal end of the first catheter (110) passes through a balloon cavity (210) of the balloon (200) and is connected with the distal end of the balloon (200); the pressure transmission cavity (101) is formed between the first conduit (110) and the second conduit (120).

10. The ablation catheter device as claimed in claim 9, wherein the catheter assembly (100) further comprises a third catheter (130), the third catheter (130) is sleeved outside the second catheter (120), a conductive cavity (103) is formed between the third catheter (130) and the second catheter (120), and a plurality of conductive wires (700) are arranged in the conductive cavity (103) corresponding to the plurality of splines (500);

the conductive wires (700) are respectively connected with the splines (500).

Images