Neural ablation device

Abstract

The present application relates to a kind of nerve ablation devices.The nerve ablation device includes support body and hanging piece, hanging piece is arranged along the circumference of support body, hanging piece is in mesh structure, hanging piece includes first area and second area arranged along the circumference of support body, the hanging piece includes the mesh structure formed by multiple mesh wires, in the first area, multiple mesh wires intersect and at least part of the mesh wires intersecting fixed connection.Thus, when support body is released in airway, support body pushes hanging piece to adhere to the inner wall of airway, when first area and second area are extruded by airway, the mesh hole area on first area reduces smaller amount, when first area and second area are electrified, the ablation energy emitted by first area is less than the ablation energy emitted by second area, so as to weaken the burning of hanging piece to esophagus.

Description

Technical Field

[0001] This invention relates to the field of medical devices, and in particular to a nerve ablation device. Background Technology

[0002] This section provides only background information relevant to this disclosure and is not necessarily prior art.

[0003] like Figure 1 , Figure 2 As shown, the cross-sectional outline of the airway 810 is approximately D-shaped. The esophagus 820 is usually attached to the flatter side of the airway 810. In the prior art, multiple electrodes 840 on the nerve ablation device are usually circumferentially distributed on the electrode support structure 830. After the electrode 840 is attached to the area to be ablated, the electrode 840 outputs RF energy from itself as the center to destroy the nerves in the tissue to achieve the effect of blocking the nerves. However, in order to ablate the area away from the electrode 840, the electrode 840 needs to output sufficient radio frequency energy to achieve ablation of the area away from the electrode 840. This results in higher radio frequency energy in the central area, which can easily cause burns to the esophagus 820 located attached to the airway 810. Summary of the Invention

[0004] Based on this, it is necessary to provide a neuroablation device, including a support body and a mounting member. The mounting member is arranged circumferentially along the support body and has a mesh structure. The mounting member includes a first region and a second region arranged circumferentially along the support body. The mounting member includes a mesh structure formed by multiple mesh wires. In the first region, the multiple mesh wires intersect and at least some of the mesh wires are fixedly connected at the intersection.

[0005] Optionally, the mesh includes braided wires, and the mesh structure is formed by weaving the braided wires.

[0006] Optionally, when the mount is subjected to pressure toward the inside of the support body, the increase in mesh density in the first region is less than the increase in mesh density in the second region.

[0007] Optionally, the nerve ablation device further includes a buffer structure disposed at the intersection of the first region and the second region, the buffer structure being used to block or reduce the transmission of force between the first region and the second region.

[0008] Optionally, the buffer structure includes a reinforcement member connected to the support and the wire mesh, extending from the support to the intersection of the first and second regions.

[0009] Alternatively, the mesh is made of a conductive material to enable the mount to form a mesh electrode.

[0010] Optionally, the stiffness of the support body at the end closer to the mounting member is less than the stiffness at the end farther from the mounting member.

[0011] Optionally, the support body has a mesh structure, and the area of ​​the smallest mesh opening at the end of the support body near the mount is larger than the area of ​​the smallest mesh opening at the end away from the mount.

[0012] Optionally, the cross-sectional area of ​​the support gradually decreases from the end closer to the mount to the end farther away from the mount.

[0013] Optionally, at least a portion of the mount is bent toward the center of the support, and the sidewall of the mount includes an arcuate surface.

[0014] Optionally, the support body includes a disc-shaped braid formed by at least one braided filament, and the hanger is disposed on the circumferential sidewall of the disc-shaped braid.

[0015] Optionally, the neuroablation device also includes a cooling balloon, which is inserted into the support body. After the cooling balloon is inflated, the sidewall of the cooling balloon fits against the sidewall of the support body.

[0016] Optionally, heat conduction holes are provided on the side wall of the support, and when the cooling bladder expands, the cooling bladder covers the heat conduction holes.

[0017] Compared with the prior art, the beneficial effects of the nerve ablation device of the present invention are: When the support is released within the airway, it pushes the mounting component to adhere to the inner wall of the airway. The first region adheres to the side wall of the airway near the esophagus, and the second region adheres to the side wall of the airway away from the esophagus. When the first and second regions are compressed by the airway, the mesh area of ​​the first region shrinks less, while the mesh area of ​​the second region shrinks more. That is, the conductive wires in the first region are sparser, while the conductive wires in the second region are denser. When the first and second regions are energized, the ablation energy emitted by the first region is less than that emitted by the second region, thereby reducing the burns to the esophagus caused by the mounting component. Attached Figure Description

[0018] Figure 1 This is a schematic diagram of the cross-sectional structure of the airway in the prior art; Figure 2 This is a schematic diagram of an electrode support structure in the prior art; Figure 3 This is a schematic diagram of the ablation device in Embodiment 1 of the present invention; Figure 4 This is a schematic diagram of the mounting component in Embodiment 1 of the present invention; Figure 5 This is a schematic diagram of the structure of the electrode emitting the ablation energy field in Embodiment 1 of the present invention; Figure 6 This is a schematic diagram of the fixed connection point in Embodiment 1 of the present invention; Figure 7 This is another structural schematic diagram of the fixed connection point in Embodiment 1 of the present invention; Figure 8 This is a schematic diagram of the structure of the mounting component under airway pressure in Embodiment 1 of the present invention; Figure 9 This is a schematic diagram of the connection structure between the mount and the support in Embodiment 1 of the present invention; Figure 10 This is a schematic diagram of a structure in the prior art where there is a gap between the electrode support and the inner wall of the airway. Figure 11 This is a schematic diagram of the connection structure of the buffer structure in Embodiment 1 of the present invention; Figure 12 For the present invention Figure 11 Enlarged schematic diagram of the structure at point C; Figure 13 This is a schematic diagram of the unfolded structure of the mounting component in Embodiment 1 of the present invention; Figure 14 This is a schematic diagram of the electrode mounting structure on the mount in Embodiment 1 of the present invention; Figure 15 This is a schematic diagram of the ablation device in Embodiment 2 of the present invention; Figure 16 This is a schematic diagram of the ablation device in Embodiment 3 of the present invention; Figure 17 This is a schematic diagram of the structure of the cooling balloon in Embodiment 4 of the present invention; Figure 18 This is a schematic diagram of the cooling conduit in Embodiment 4 of the present invention. Detailed Implementation

[0019] To make the above-mentioned objects, features, and advantages of the present invention more apparent and understandable, specific embodiments of the present invention will be described in detail below with reference to the accompanying drawings. Many specific details are set forth in the following description to provide a thorough understanding of the present invention. However, the present invention can be practiced in many other ways different from those described herein, and those skilled in the art can make similar modifications without departing from the spirit of the present invention. Therefore, the present invention is not limited to the specific embodiments disclosed below.

[0020] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains. The terminology used herein in the description of the invention is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention.

[0021] Example 1 Embodiments of the present invention provide an ablation device, such as Figures 3 to 9As shown, it includes a support body 110 and a mounting member 120. The mounting member 120 is arranged circumferentially along the support body 110. The mounting member 120 has a mesh structure and includes a first region 121 and a second region 122. When the mounting member 120 is squeezed by the air passage 810, the increase in mesh density of the first region 121 is less than the increase in mesh density of the second region 122.

[0022] The ablation device generates ablation energy at the site of tissue to be ablated in the human body. This ablation energy can ablate nerves within the tissue, thereby achieving the therapeutic effect on the affected area. The ablation device can be used for ablation of areas such as the airway, heart, aorta, and stomach. For example, in this embodiment, the ablation device is delivered to the airway 810 via a delivery device, and then the ablation device ablates the nerves in the airway 810 tissue, thereby expanding the airway 810 and achieving the treatment of lung diseases.

[0023] The support 110 includes a loaded state and an expanded state. When the support 110 is located inside the conveying device, it is in the loaded state, in which case it is compressed within the sheath of the conveying device to facilitate its conveying. When the support 110 is released within the air passage 810, it expands, causing the mounting member 120 to adhere to the inner wall of the air passage 810.

[0024] The support 110 can be tubular, rod-shaped, disc-shaped, or cube-shaped. It can be formed by cutting shape-memory metal or weaving filaments. The support 110 has a certain degree of elasticity. When the mounting component 120 is compressed by the air passage 810, the support 110 provides elastic support to the mounting component 120, ensuring the contact area between the mounting component 120 and the inner wall of the air passage 810.

[0025] The mounting component 120 can be woven, cut from metal, or made of a conductive material to form a mesh structure. The mounting component 120 surrounds the support body 110 and can be wound around, welded to, or integrally connected to the support body 110. The outer wall of the mounting component 120 has a mesh structure and fits against the inner wall of the airway 810. In other embodiments, one axial end of the support body 110 is radially bent outward and heat-set to form the mounting component 120. The mounting component 120 is used to mount the electrode 840. After the electrode 840 is mounted on the mounting component 120, it forms an ablation energy field to achieve ablation of the airway 810 tissue.

[0026] In this embodiment, both the mounting element 120 and the support body 110 are formed by braiding conductive wires. The exposed conductive wires on the mounting element 120 form a mesh electrode 840; the outer wall of the conductive wires on the support body 110 is covered with an insulating layer. When the conductive wires are energized, the mesh electrode 840 formed by the mounting element 120 outputs radio frequency energy to destroy the nerves in the airway 810 tissue.

[0027] The conductive wire can be a nickel-titanium alloy wire, stainless steel wire, or any other conductive filament. One end of the conductive wire is connected to an RF (Radio Frequency) power meter, which provides electrical energy to the conductive wire. The electrical energy passes through the support 110 and is then transmitted to the mounting component 120 to form an ablation energy field 700. Figure 5 As shown, the ablation energy field 700 is centered on the support 110 and then diffuses radially outward layer by layer from the part where the mount 120 is attached to the airway 810.

[0028] like Figure 5 As shown, the mounting component 120 can be roughly regarded as a point electrode. In this way, a continuous annular ablation energy field 700 can be formed with the mounting component 120 as the center and the position where the mounting component 120 is attached to the airway 810 as the starting point. Compared with the ablation method in which multiple point electrodes 840 generate multiple overlapping annular energy fields, the energy of the mesh electrode is more uniform and it is easier to control the output ablation energy, thereby reducing the probability of the ablation device burning the airway 810.

[0029] Furthermore, in order to reduce damage to the esophagus 820 during the ablation process, such as... Figure 4 As shown, the mounting component 120 includes a first region 121 and a second region 122 arranged circumferentially along the support body 110. When the mounting component 120 is squeezed by the air passage 810, the increase in mesh density of the first region 121 is less than the increase in mesh density of the second region 122.

[0030] It should be noted that the mesh density in this embodiment refers to the number of mesh openings per unit area. The increase in mesh density refers to the difference between the number of mesh openings per unit area when the support 110 is not compressed and the number of mesh openings per unit area after the support 110 is compressed. The first region 121 and the second region 122 are arranged circumferentially along the hanger 120, and the ratio of the circumferential length of the first region 121 and the second region 122 is 0.3 to 1; specifically, the ratio of the circumferential length of the first region 121 and the second region 122 is 0.3, 0.5, 0.6, 0.8 or 1.

[0031] It is worth explaining that mesh density can be measured using electron microscopy and photographic measurement methods. For example, in one embodiment, a transparent first fixture in the shape of a cuboid is provided. The first fixture has a first cavity structure corresponding to the outline of the hanger 120. Multiple measuring squares with the same area are provided on the outer wall of the first fixture. After the hanger 120 is released into the first cavity structure, the side wall of the hanger 120 is attached to the inner wall of the first cavity structure but there is no interaction force. The first fixture is magnified by a certain magnification using an electron microscope, and the number of meshes t1 in a single measuring square is calculated using the mesh count method. A second fixture corresponding to the airway cross-section is provided. The second fixture has a second cavity structure corresponding to the airway outline. Multiple measuring squares with the same area are provided on the outer wall of the second fixture. The hanger 120 is released into the second cavity structure and is attached to the inner wall of the second cavity structure. The second fixture is magnified by a certain magnification using an electron microscope, and the number of meshes t2 in a single measuring square is calculated using the mesh count method. The increase in mesh area is t2-t1. In this embodiment, the mounting element 120 includes multiple mesh wires forming a mesh structure. The mesh wires are woven from braided wires, which can be conductive wires, nickel-titanium alloy wires, or stainless steel wires. For example, in the first region 121, such as... Figure 6 , Figure 7 As shown, the conductive wires intersect and are fixedly connected, while in the second region 122, the conductive wires intersect and are movably connected. For example, in the first region 121, the conductive wires intersect to form a grid or mesh, and the two intersecting conductive wires are welded or wrapped together at the fixed connection point 126. Thus, as... Figure 8 , Figure 9 As shown, in the first region 121, when the conductive wire is compressed, the two intersecting conductive wires are fixed, thus the displacement of the adjacent conductive wires moving towards each other is small or remains unchanged. Consequently, the area of ​​the mesh s1 in the first region 121 remains unchanged or the reduction in the mesh area s1 is small, resulting in a small increase in the mesh density in the first region 121. In the second region 122, the two intersecting conductive wires are in contact with each other. The two intersecting conductive wires can move away from each other or towards each other. Thus, in the second region 122, when the conductive wire is compressed, the displacement of the two intersecting conductive wires moving towards each other is large, resulting in a larger reduction in the mesh area s2 in the second region 122, that is, a larger increase in the mesh density in the second region 122.

[0032] In another embodiment, the mounting member 120 includes mesh wires cut from metal material. For example, in one embodiment, the first region 121 is formed by cutting metal material into arc-shaped mesh wires, and the second region 122 is formed by weaving conductive wires into an arc-shaped mesh structure. The conductive wires on the second region 122 intersect and are movably connected, and the two ends of the first region 121 and the second region 122 are attached together in the length direction. Thus, when the first region 121 and the second region 122 are compressed by the air passage 810, the first region 121, being formed by cutting metal material, allows the mesh area s1 to remain unchanged when compressed. The second region 122, being formed by weaving conductive wires with intersecting and movably connected conductive wires, results in a larger reduction in mesh size s2 when compressed by the air passage 810. This achieves a smaller increase in mesh density in the first region 121 than in the second region 122.

[0033] The advantage of this arrangement is that when the support 110 is released within the airway 810, the support 110 pushes the mounting member 120 to adhere to the inner wall of the airway 810. Specifically, the first region 121 adheres to the side wall of the airway 810 near the esophagus 820, and the second region 122 adheres to the side wall of the airway 810 away from the esophagus 820. When the first region 121 and the second region 122 are compressed by the airway 810, the mesh area on the first region 121 shrinks less, while the mesh area on the second region 122 shrinks more. That is, the conductive wires on the first region 121 are sparser, while the conductive wires on the second region 122 are denser. When the first region 121 and the second region 122 are energized, the ablation energy emitted by the first region 121 is less than that emitted by the second region 122, thereby reducing the burns to the esophagus 820 caused by the mounting member 120.

[0034] Furthermore, in order to reduce the interference of the support 110 on the deformation of the first region 121, the stiffness of the end of the support 110 near the mount 120 is less than the stiffness of the end away from the mount 120.

[0035] In this embodiment, as Figure 9 As shown, the support body 110 has a mesh structure. The support body 110 includes a first end 111 and a second end 112. The first end 111 is connected to the hanger 120. The area of ​​the smallest mesh on the first end 111 is larger than the area of ​​the smallest mesh on the second end 112.

[0036] It should be noted that the first end 111 refers to the end covered by the radial projection of the hanger 120 onto the support 110, and the second end 112 refers to the end of the support 110 away from the hanger 120. The smallest mesh size on the first end 111 refers to the area S3 of the smallest mesh size formed by the intersection of the conductive wires on the first end 111, and the smallest mesh size on the second end 112 refers to the area S4 of the smallest mesh size formed by the intersection of the conductive wires on the second end 112. The area of ​​the smallest mesh size on the first end 111 is greater than the area of ​​the smallest mesh size on the second end 112, that is, the area of ​​any mesh size on the first end 111 is greater than the area of ​​the mesh size on the second end 112.

[0037] The mesh area on the first end 111 is larger, meaning the density of the braided filaments on the first end 111 is lower. In this case, the deformation performance of the first end 111 is greater than that of the second end 112. When the hanger 120 is squeezed by the air passage 810, the first end 111 can deform along with the second end 112, avoiding interference between the support body 110 and the deformation of the hanger 120. This makes it easier for the hanger 120 to adapt to the D-shaped contour of the air passage 810 and increases the wall adhesion of the hanger 120. The mesh area on the second end 112 is smaller, meaning the density of the conductive filaments on the second end 112 is lower. In this case, the deformation resistance of the second end 112 is greater than that of the first end 111. Thus, the second end 112 can provide support for the first end 111, increasing the stability of the transport and release of the support body 110.

[0038] In another embodiment, the diameter of the braided wire at the first end 111 is smaller than the diameter of the braided wire at the second end 112. Since the stiffness of the braided wire with a larger diameter is greater than the stiffness of the braided wire with a smaller diameter, the stiffness at the first end 111 is greater than the stiffness at the second end 112. This achieves the setting that the stiffness of the support body 110 near the hanger 120 is less than the stiffness of the end away from the hanger 120.

[0039] In other embodiments, the braided filaments at the first end 111 intersect and are movably connected, while the braided filaments at the second end 112 intersect and are fixedly connected. Since the deformation resistance of the fixedly connected braided filaments is greater than that of the intersecting and movably connected braided filaments, the stiffness at the first end 111 is greater than that at the second end 112. This achieves the setting that the stiffness of the support body 110 near the hanger 120 is less than the stiffness of the end away from the hanger 120.

[0040] It is worth explaining that, due to the high stress on the support body 110 when it is loaded, the support body 110 is prone to instantaneous expansion and instability when it is released in the air passage 810. At this time, the second end 112 has high rigidity and strong support force, which can slow down the deformation rate of the first end 111 when it is released, thereby making the first end 111 more stable when it is released.

[0041] Furthermore, in order to reduce the difficulty of loading the ablation device into the delivery device, such as... Figure 9 As shown, the cross-sectional area of ​​the support 110 gradually decreases from the first end 111 to the second end 112. In this embodiment, the cross-sectional area of ​​the support 110 refers to the cross-sectional area of ​​the support 110 in the radial plane. The cross-sectional area of ​​the support 110 gradually decreases from the first end 111 to the second end 112, so that the support 110 as a whole presents a frustum-shaped structure.

[0042] Because the conductive wires at the second end 112 are relatively dense, it is more difficult for the support body 110 to enter the sheath of the conveying device. The cross-sectional area of ​​the support body 110 gradually decreases from the first end 111 to the second end 112, making the transverse area of ​​the support body 110 at the second end 112 smaller, thereby reducing the difficulty of the second end 112 entering the sheath.

[0043] It is worth explaining, such as Figure 10 As shown, for the annular electrode support structure 830, when the electrode support structure 830 is released within the airway 810, the pressure of the smooth muscle 812 of the airway 810 on the electrode support structure 830 is greater than the pressure of the C-shaped region of the airway 810 on the electrode support structure 830. The deformation of the electrode support structure 830 on the side closer to the smooth muscle 812 is greater than the deformation of the electrode support structure 830 on the side closer to the C-shaped region. At this time, the deformation of the electrode support structure 830 on the side closer to the smooth muscle 812 will cause the electrode support structure 830 on the side closer to the C-shaped region to deform excessively. As a result, a gap s3 is formed between the electrode support structure 830 and the inner wall of the airway 810 at the transition area where the C-shaped region connects to the smooth muscle 812, making it difficult to ablate the airway at the gap s3.

[0044] Furthermore, to facilitate the fitting of the mount 120 with the D-shaped contour of the air duct 810, such as Figure 11 As shown, the ablation device also includes a buffer structure 130, which is connected to the mount 120 at the connection point of the first region 121 and the second region 122.

[0045] In one embodiment, such as Figure 11As shown, the buffer structure 130 includes a reinforcing rod 131, which is welded or inserted into the support body 110 and extends along the side wall of the support body 110 to the hanger 120. The reinforcing rod 131 forms an anti-deformation support at the connection node of the first region 121 and the second region 122, which weakens or blocks the force transmission from the first region 121 to the second region 122. Thus, when the first region 121 is squeezed by the smooth muscle 812, the reinforcing rod 131 blocks or weakens the pull of the first region 121 on the second region 122, so that the second region 122 is not affected by the deformation of the first region 121, so that the second region 122 can keep in contact with the C-shaped contour 811, thereby improving the wall-fitting performance of the hanger 120.

[0046] In another embodiment, such as Figure 12 As shown, the buffer structure 130 includes reinforcing ribs 132. In the region where the first region 121 and the second region 122 meet, the reinforcing ribs 132 are located within the mesh and connected to the braided wires that intersect the mesh at both ends of the hanger 120 in the circumferential direction. The mesh in the region where the first region 121 and the second region 122 meet includes a first intersection point 123 and a second intersection point 124 where the braided wires intersect. The first intersection point 123 and the second intersection point 124 are arranged along the circumferential direction of the hanger 120. The reinforcing ribs 132 include a first reinforcing rib 1321 and a second reinforcing rib 1322. The two ends of the first reinforcing rib 1321 are connected to two braided wires at the first intersection point 123, and the two ends of the second reinforcing rib 1322 are connected to two braided wires at the second intersection point 124. Both the first reinforcing rib 1321 and the second reinforcing rib 1322 have an arc-shaped structure, and the arc-shaped convex surfaces of the first reinforcing rib 1321 and the second reinforcing rib 1322 are arranged opposite each other. In this way, by setting the reinforcing rib 132, the reinforcing rib 132 can form an anti-deformation support at the junction of the first region 121 and the second region 122, blocking or weakening the force transmission from the first region 121 to the second region 122, so that the second region 122 will not be affected by the deformation of the first region 121, so that the second region 122 remains in close contact with the C-shaped contour 811, improving the wall-fitting performance of the mounting component 120.

[0047] Furthermore, such as Figure 13 As shown, the mounting component 120 also includes a third region 125, which is located between the first region 121 and the second region 122. The third region 125 forms a free segment to mitigate the force transmission from the first region 121 to the second region 122. It can be understood that the structure in which the third region 125 forms a free segment is one embodiment of the buffer structure 130.

[0048] In this embodiment, the free segment refers to the unconstrained segment, that is, at the third region 125, the force transmission effect is low. Specifically, the braided filaments at the third region 125 intersect and are movably connected. The mesh area formed by the intersecting braided filaments is much larger than the mesh area of ​​any mesh in the first region 121 and / or the second region 122. Thus, at the third region 125, the density of the braided filaments is low, which weakens the force transmission effect from the first region 121 to the second region 122. This prevents the second region 122 from being affected by the deformation of the first region 121, allowing the second region 122 to remain in close contact with the C-shaped contour 811, thereby improving the wall adhesion of the mount 120.

[0049] Furthermore, the ratio of the circumferential length of the second region 122 to that of the first region 121 is 1.1-4. Specifically, the ratio of the circumferential length of the second region 122 to that of the first region 121 can be 1.1, 1.5, 2, 3, or 4. Thus, by setting the ratio of the circumferential length of the second region 122 to that of the first region 121, the transition region between the first region 121 and the second region 122 corresponds to the transition region between the C-shaped contour 811 and the smooth muscle 812 of the airway 810, thereby improving the adaptability to the airway 810.

[0050] Furthermore, in order to reduce the friction between the mounting components and the inner wall of the air passage, such as Figure 14 As shown, the mounting component 120 has an arc-shaped structure, with the convex surface of the arc-shaped structure facing away from the support body 110.

[0051] In this embodiment, the mounting element 120 is bent outward from one axial end of the support body 110 and then bent inward towards the support body 110, and finally formed by heat setting. During the release of the support body 110 into the airway 810, the mounting element 120 may not be in contact with the target area. In this case, the operator needs to move the mounting element 120 to make it fit the target area. During the movement of the mounting element 120, the friction between the end of the mounting element 120 and the airway 810 is relatively large, which may easily cause friction against the airway 810 or cause discomfort to the patient.

[0052] Therefore, by making the mounting component 120 arc-shaped, the arc-shaped structure can fit against the inner wall of the airway 810, increasing the contact area between the arc-shaped structure and the inner wall of the airway 810, and reducing the friction between the mounting component 120 and the inner wall of the airway 810. By setting the convex surface of the arc-shaped structure towards the side away from the support body 110, the end of the mounting component 120 faces the inner side of the support body 110. During the movement of the mounting component 120, friction between the end of the mounting component 120 and the airway 810 can be avoided, thus preventing discomfort to the patient.

[0053] In other embodiments, such as Figure 14As shown, the ablation device includes an electrode 840, which is disposed on the mounting member 120. The electrode 840 can be a strip electrode 840 or a point electrode 840. The electrode 840 is disposed on the mounting member 120 along the circumference of the support 110. The electrode 840 can be welded or wrapped around the mounting member 120. The electrode 840 is connected to an RF energy meter, which powers the electrode 840 to emit an ablation energy field 700.

[0054] The advantage of this design is that when the mounting component 120 is compressed by the airway 810, the braided filaments on the first region 121 intersect and are fixedly connected, while the braided filaments on the second region 122 intersect and are movably connected. This results in the mesh size reduction on the first region 121 being smaller than that on the second region 122. In other words, the amount of movement of the different electrodes 840 on the first region 121 towards each other is smaller or unchanged, while the amount of movement of the different electrodes 840 on the second region 122 towards each other is larger. Consequently, the degree of overlap of the energy fields of the electrodes 840 on the first region 121 is lower than that of the electrodes 840 on the second region 122. This means that the ablation energy emitted by the first region 121 is less than that emitted by the second region 122, thus reducing the burns caused by the mounting component 120 to the esophagus 820.

[0055] Example 2 The difference between this embodiment and Embodiment 1 is that, as Figure 15 As shown, the mounting component 220 includes multiple ablation units 221 arranged circumferentially along the support body 210. Two circumferentially adjacent ablation units 221 are spaced apart. The ablation units 221 are disposed on the support body 210 and are respectively located on the first region 222 and / or the second region 223.

[0056] In this embodiment, the mounting member 220 forms multiple ablation units 221 during the weaving process. The ablation units 221 have a mesh structure and arc-shaped edges. Adjacent ablation units 221 are spaced apart in the portion away from the support 210 to allow for deformation space. The ablation units 221 can be simultaneously disposed on the first region 222 or the second region 223, or only disposed on the first region 222.

[0057] For example, in one embodiment, the ablation unit 221 includes a first ablation unit 224 and a second ablation unit 225. The first ablation unit 224 is located on a first region 222, and the second ablation unit 225 is located on a second region 223. The conductive wires on the first ablation unit 224 intersect and are fixedly connected, and the conductive wires on the second ablation unit 225 intersect and are movably connected. There is a certain interval between two circumferentially adjacent ablation units 221.

[0058] Thus, when the mount 220 is compressed by the airway, there is a gap between the two adjacent ablation units 221 to block or weaken the force transmission between the two adjacent ablation units 221. When the ablation unit 221 is compressed by the smooth muscle 812, on the one hand, the ablation unit 221 will not be interfered with by the adjacent ablation unit 221 and will not extend to both ends, so that the ablation unit 221 can more easily fit into the smooth muscle 812. On the other hand, the ablation unit 221 will not cause the adjacent ablation unit 221 to deform, thereby avoiding the ablation unit 221 on the side away from the smooth muscle 812 from being stretched and excessively deformed, making it difficult to fit into the C-shaped contour 811, thereby improving the adaptability of the mount 220 to the D-shaped contour of the airway.

[0059] Furthermore, such as Figure 15 As shown, the support body 210 includes a plurality of support members 211, which are spaced apart along the circumferential direction of the mounting member 220, and each ablation unit 221 is connected to at least two support members 211. In this embodiment, the support body 210 is formed by laser cutting of metal material. The support members 211 are arranged at equal or non-equal intervals along the circumference of the hanger 220. This embodiment does not limit the number of support members 211. For example, in one embodiment, the support member 211 includes a first support arm 2111 and a second support arm 2112. One end of the first support arm 2111 and one end of the second support arm 2112 are connected to form a V-shaped structure. The other ends of the first support arm 2111 and the second support arm 2112 are connected to the ablation unit 221. The opening of the V-shaped structure faces the side closer to the ablation unit 221. The two ends of each V-shaped structure are respectively connected to two adjacent ablation units 221. Multiple V-shaped structures are arranged along the circumference of the hanger 220.

[0060] Thus, a V-shaped structure is formed by connecting the first support arm 2111 and the second support arm 2112. On the one hand, there is a gap between the first support arm 2111 and the second support arm 2112 to allow space for the two ends of the ablation unit 221 to deform and elongate, so that the ablation unit 221, which is in contact with the smooth muscle 812, can be deformed under pressure to fit with the smooth muscle 812. On the other hand, when the first region 222 is deformed by the airway, the force transmission between the two adjacent ablation units 221 is interrupted by the gap between the first support arm 2111 and the second support arm 2112, thereby increasing the adaptability of the mount 220 to the inner wall of the D-shaped contour of the airway.

[0061] In another embodiment, the support member 211 is a rod-shaped structure, and each support member 211 is connected to only one ablation unit 221. Each ablation unit 221 is connected to at least two adjacent support members 211. The two adjacent support members 211 are spaced apart, so that a gap can also be formed between the two adjacent support members 211, thereby blocking the force transmission between the two adjacent ablation units 221 and increasing the adaptability of the mount 220 to the D-shaped profile of the airway.

[0062] Furthermore, the spacing between two adjacent ablation units 221 is 0.2~1mm. Thus, by limiting the spacing between two adjacent ablation units 221, when two adjacent ablation units 221 are deformed under pressure, the ends of the two adjacent ablation units 221 can fit together to form a continuous ablation zone in the circumferential direction.

[0063] Example 3 The difference between this embodiment and Embodiment 1 is that, as Figure 16 As shown, the support 310 includes multiple braided filaments, which are woven together to form a disc-shaped braided body 330. The circumferential edge 320 of the disc-shaped braided body 330 forms a hanger. The first region and the second region are located on the circumferential edge 320 of the disc-shaped braided body 330.

[0064] In this embodiment, the braided filaments of the disc-shaped braid 330 are conductive filaments, and the circumferential edge 320 of the disc-shaped braid 330 is exposed. After being energized, the exposed portion forms a mesh electrode. In other embodiments, the outer wall of the disc-shaped braid 330 is covered with an insulating layer, or the braided filaments of the disc-shaped braid 330 are made of a non-conductive material, and the electrode is disposed on the outer wall of the disc-shaped braid 330 to form a mounting member. In the first region, the braided filaments intersect and are fixedly connected, and in the second region, the braided filaments intersect and are movably connected. The first and second regions are arranged along the circumference of the disc-shaped braid 330, and the length ratio of the first and second regions is similar to that of Embodiment 1, and will not be repeated here.

[0065] Thus, the support body 310 is woven into a disc-shaped braid 330 by braiding filaments. The disc-shaped braid 330 has good radial support force. When the mount is squeezed by the inner wall of the airway, the support body 310 provides sufficient support force to make the mount fit against the inner wall of the airway.

[0066] Furthermore, the ablation device includes an adjustment member 340, one end of which is connected to one axial end of the disc-shaped braid 330, and the other end of which extends out of the sleeve 350. The adjustment member 340 is used to adjust the diameter of the disc-shaped braid 330.

[0067] In this embodiment, both axial ends of the disc-shaped braid 330 extend outward from the axial direction of the disc-shaped braid 330 to allow for deformation space for adjusting the diameter of the disc-shaped braid 330. One end of the adjusting member 340 is threaded or welded to one axial end of the disc-shaped braid 330, and the other end of the adjusting member 340 extends out from the sleeve 350.

[0068] In one embodiment, when it is necessary to increase the diameter of the disc-shaped braid 330, the adjusting member 340 is pulled to move the two axial ends of the disc-shaped braid 330 toward each other, thereby increasing the diameter of the disc-shaped braid 330; when it is necessary to decrease the diameter of the disc-shaped braid 330, the adjusting member 340 is pushed to move the two axial ends of the disc-shaped braid 330 away from each other, thereby decreasing the diameter of the disc-shaped braid 330.

[0069] The advantage of this design is that when the support 310 deviates from the target position after being released in the trachea, the diameter of the disc-shaped braid 330 can be adjusted by the adjusting member 340 to reduce the diameter of the disc-shaped braid 330 so as to facilitate the adjustment of the position of the disc-shaped braid 330 in the airway, thereby reducing the difficulty of adjusting the position of the support 310 in the airway.

[0070] Example 4 The difference between this embodiment and Embodiment 1 is that, as Figure 17 As shown, the ablation device includes a cooling balloon 430, which is inserted into the support 410. When the cooling balloon 430 expands, it at least partially covers the mesh on the mounting member 420.

[0071] In this embodiment, the cooling balloon 430 is used to contain the cooling medium. One end of the delivery channel 440 is located inside the balloon, and the other end of the delivery channel 440 extends out from the sleeve 450. Cooling medium can be introduced into the balloon through the conduit to cool the electrode and the part to be ablated. The cooling medium can be a gaseous cooling medium or a liquid cooling medium. Specifically, the cooling medium can be at least one of CO2 gas flow, physiological saline or pure water.

[0072] The sidewalls of the support body 410 and the mounting component 420 have a mesh structure, and the mesh openings form heat-conducting holes. During the ablation of the airway, a cooling medium is introduced into the cooling balloon 430, causing the balloon to expand. After expansion, the cooling balloon 430 fits against the sidewalls of the support body 410 and the mounting component 420, and covers the mesh openings of the support body 410 and the mounting component 420, so that the sidewall of the cooling balloon 430 fits against the inner wall of the airway. Heat on the inner wall of the airway can be transferred to the cooling balloon 430 through the heat-conducting holes, increasing the heat conduction efficiency and improving the cooling effect of the balloon. After the airway ablation is completed, the cooling medium inside the balloon is extracted, causing the balloon to contract, and then the balloon and the support body 410 are removed.

[0073] Therefore, when the cooling balloon 430 expands, it passes through the support body 410. The side wall of the cooling balloon 430 can cover the mesh of the support body 410 and the hanger 420, so that the side wall of the cooling balloon 430 can fit against the inner wall of the airway, thereby achieving cooling of the electrode and the inner wall of the airway and avoiding excessive ablation temperature that could burn the inner wall of the airway.

[0074] In other embodiments, such as Figure 18 As shown, the ablation device includes a cooling conduit 460, which surrounds the support 410 and is located inside the mounting member 420. The outer wall of the cooling conduit 460 is in contact with the inner wall of the mounting member 420. The cooling conduit 460 has injection holes, the positions of which correspond to the positions of the mesh holes on the mounting member 420. The cooling medium passes through the injection holes and through the mesh holes on the mounting member 420 to be sprayed onto the inner wall of the airway, thereby cooling the inner wall of the airway and preventing the ablation temperature from being too high and burning the inner wall of the airway.

[0075] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0076] The embodiments described above are merely illustrative of several implementations of the present invention, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the invention patent. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of the present invention, and these all fall within the protection scope of the present invention. Therefore, the protection scope of this invention patent should be determined by the appended claims.

Claims

1. A nerve ablation device, characterized in that, The device includes a support body and a mounting component. The mounting component is arranged circumferentially along the support body and has a mesh structure. The mounting component includes a first region and a second region arranged circumferentially along the support body. The mounting component includes a mesh structure formed by multiple mesh wires. In the first region, the multiple mesh wires intersect and are fixedly connected at at least some of the intersections. When the mounting component is subjected to pressure toward the inside of the support body, the increase in mesh density in the first region is less than the increase in mesh density in the second region. The mesh wires are made of a conductive material to enable the mounting component to form a mesh electrode.

2. The neuroablation device according to claim 1, characterized in that, The mesh includes braided wires, and the mesh structure is formed by weaving the braided wires.

3. The neuroablation device according to claim 1, characterized in that, The neuroablation device further includes a buffer structure located at the intersection of the first region and the second region. The buffer structure is used to block or reduce the transmission of force between the first region and the second region.

4. The neuroablation device according to claim 3, characterized in that, The buffer structure includes a reinforcing member connected to the support and the mesh, and extending from the support to the intersection of the first region and the second region.

5. The neuroablation device according to claim 1, characterized in that, The stiffness of the support body at the end closer to the mounting member is less than the stiffness at the end farther away from the mounting member.

6. The neuroablation device according to claim 5, characterized in that, The support body has a mesh structure, and the area of ​​the smallest mesh hole at the end of the support body near the mounting member is larger than the area of ​​the smallest mesh hole at the end away from the mounting member.

7. The neuroablation device according to claim 1, characterized in that, The cross-sectional area of ​​the support gradually decreases from the end closer to the mounting member to the end farther away from the mounting member.

8. The neuroablation device according to claim 1, characterized in that, At least a portion of the mounting member is bent toward the center of the support body, and the sidewall of the mounting member includes an arcuate surface.

9. The neuroablation device according to claim 1, characterized in that, The support body includes a disc-shaped braided body formed by at least one braided filament, and the hanger is disposed on the circumferential sidewall of the disc-shaped braided body.

10. The neuroablation device according to claim 1, characterized in that, The neuroablation device also includes a cooling balloon, which is inserted into the support body. After the cooling balloon is inflated, the sidewall of the cooling balloon fits against the sidewall of the support body.

11. The neuroablation device according to claim 10, characterized in that, The support body has heat conduction holes on its side wall. When the cooling bladder expands, the cooling bladder covers the heat conduction holes.

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