Ablation catheter and ablation device

Abstract

The present application is applicable to the technical field of medical devices, and provides an ablation catheter (100) and an ablation device. The ablation catheter (100) comprises: a catheter assembly (10); and an ultrasonic generator (20) arranged in the catheter assembly, wherein the ultrasonic generator comprises a driving assembly (21) and a generation assembly (22) connected to the driving assembly, the driving assembly is used for driving the generation assembly to vibrate, the generation assembly is used for emitting ultrasonic waves and converging the ultrasonic waves to a focus, and the focus is arranged outside the catheter assembly. The ablation device comprises the ablation catheter. According to the ablation catheter provided by the present application, the ultrasonic waves emitted by the generation assembly can be converged outside a blood vessel wall to form a focus, so that the ultrasonic waves can have larger energy at the focus to ablate sympathetic nerves at the corresponding position; moreover, at the position where the ultrasonic waves pass through the blood vessel wall, the ultrasonic waves are dispersed and carry less energy, resulting in less heating of the blood vessel wall, thus alleviating the damage caused by the ultrasonic waves to the blood vessel wall.

Description

Ablation catheters and ablation equipment Technical Field

[0001] The present application relates to the technical field of medical equipment, and in particular to an ablation catheter and an ablation device. Background Art

[0002] Renal artery denervation (RDN) refers to a method of destroying renal sympathetic afferent and efferent nerves through interventional therapy (such as through the femoral artery or radial artery), weakening renal and systemic sympathetic nerve activity, and thus lowering blood pressure.

[0003] RDN techniques can be based on radiofrequency ablation, ultrasound ablation, cryoablation, and chemical ablation, but currently, radiofrequency ablation (rRDN) and ultrasound ablation (uRDN) are the dominant approaches. Ultrasound ablation, with its advantages of good penetration and high energy controllability, holds certain technical advantages in the RDN field.

[0004] Currently, ultrasound ablation primarily utilizes two approaches: a circular transducer with 360° energy emission and a planar transducer with directional energy emission. However, the ultrasonic energy distribution of either the circular or planar transducer is incapable of protecting the renal artery wall, necessitating the reliance on other cooling methods to achieve this, which increases the risk of renal artery damage and stenosis. Technical issues

[0005] The purpose of the present application is to provide an ablation catheter and an ablation device, aiming to alleviate the negative impact of ultrasound on the renal artery vascular wall during the process of ablating the renal artery sympathetic nerves. Technical Solutions

[0006] In a first aspect, some embodiments of the present application provide an ablation catheter, comprising:

[0007] catheter components;

[0008] The ultrasonic generating device is arranged in the catheter assembly. The ultrasonic generating device includes a driving assembly and a generating assembly connected to the driving assembly. The driving assembly is used to drive the generating assembly to vibrate. The generating assembly is used to emit ultrasonic waves and converge the ultrasonic waves at a focus. The focus is set outside the catheter assembly.

[0009] In some embodiments, the generating component includes an arc-shaped piezoelectric piece, and the center and focus of the piezoelectric piece are located on the same side of the catheter component.

[0010] In some embodiments, the radius of the piezoelectric piece ranges from 6 mm to 15 mm.

[0011] In some embodiments, at least one partition groove is provided on the piezoelectric sheet, and the partition groove can separate the piezoelectric sheet into at least two piezoelectric sub-sheets, and the piezoelectric sub-sheets can rotate relative to the driving assembly.

[0012] In some embodiments, the generating component includes a first state and a second state, and the acoustic power of the ultrasonic wave emitted by the generating component in the second state is less than or equal to 10% of the acoustic power of the ultrasonic wave emitted by the generating component in the first state.

[0013] In some embodiments, the ablation catheter further includes an imaging device, which is disposed in the catheter assembly and beside the ultrasound generating device.

[0014] In some embodiments, the catheter assembly includes an outer tube and a rotating member disposed in the outer tube, wherein a receiving cavity is disposed in the outer tube, and the ultrasonic generating device is accommodated in the receiving cavity;

[0015] One end of the rotating member extends into the accommodating cavity and is connected to the ultrasonic generating device. The rotating member can bend along with the outer tube, and can rotate relative to the outer tube and drive the ultrasonic generating device to rotate.

[0016] In some embodiments, the catheter assembly further includes a liquid inlet channel and a liquid discharge channel provided on the outer tube, and one end of the liquid inlet channel and the liquid discharge channel are both connected to the accommodating cavity.

[0017] In some embodiments, the catheter assembly further comprises a covering membrane arranged around the outer tube, the covering membrane forming a covering cavity outside the outer tube, the covering cavity being connected to the accommodating cavity, and the covering membrane being able to move toward or away from the accommodating cavity.

[0018] In some embodiments, the catheter assembly further comprises a support member and a movable member disposed outside the outer tube, one end of the support member being connected to the outer tube, and the other end of the support member being connected to the movable member;

[0019] The movable member is movably connected to the outer tube. The movable member can move relative to the outer tube along the axial direction of the outer tube and can drive the supporting member to deform in a direction away from or close to the outer tube.

[0020] In some embodiments, the outer tube is provided with an opening communicating with the accommodating cavity, and the opening is opposite to the ultrasonic generating device;

[0021] A sound-transmitting film is provided on the opening, and is used to seal the opening and allow ultrasonic waves to pass through.

[0022] In some embodiments, the ablation catheter further includes a temperature sensor, which is disposed beside the ultrasound generating device.

[0023] In a second aspect, some embodiments of the present application further provide an ablation device, including the ablation catheter provided by some embodiments of the first aspect. Beneficial effects

[0024] Compared with the prior art, the embodiments of the present application have the following beneficial effects: the ultrasonic generating device includes a driving component and a generating component, and the ultrasonic waves emitted by the generating component can converge outside the blood vessel wall to form a focus, so that the ultrasonic waves can have greater energy at the focus to ablate the sympathetic nerves at the corresponding position; and at the position where the ultrasonic waves pass through the blood vessel wall, the ultrasonic waves are more dispersed and carry lower energy, so that the blood vessel wall heats up less, thereby alleviating the damage of the ultrasonic waves to the blood vessel wall. BRIEF DESCRIPTION OF THE DRAWINGS

[0025] In order to more clearly illustrate the technical solutions in the embodiments of the present application, the following briefly introduces the drawings required for use in the embodiments or descriptions of the prior art. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without any creative work.

[0026] FIG1 is a partial three-dimensional schematic diagram of an ablation catheter provided in some embodiments of the present application.

[0027] FIG2 is a partial three-dimensional schematic diagram of an ablation catheter provided in some embodiments of the present application.

[0028] FIG3 is a schematic cross-sectional view of the ablation catheter shown in FIG1 .

[0029] FIG4 is a partial enlarged schematic diagram of point A in FIG3 .

[0030] FIG5 is a schematic cross-sectional view of a section BB in FIG3 .

[0031] FIG6 is a schematic cross-sectional view of the ablation catheter shown in FIG2 .

[0032] FIG7 is a partial enlarged schematic diagram of point C in FIG6 .

[0033] FIG8 is a schematic cross-sectional view of a portion DD in FIG6 .

[0034] FIG9 is a three-dimensional schematic diagram of an ultrasound generating device in an ablation catheter provided in some embodiments of the present application.

[0035] FIG10 is a schematic diagram of the structure of a piezoelectric piece in an ablation catheter provided in some embodiments of the present application.

[0036] FIG11 is a three-dimensional schematic diagram of an ablation device provided in some embodiments of the present application.

[0037] The meanings of the marks in the figure are:

[0038] 100. Ablation catheter;

[0039] 10. Catheter assembly; 11. Outer tube; 111. Accommodating cavity; 112. Opening; 113. End piece; 12. Rotating member; 13. Liquid inlet channel; 14. Liquid discharge channel; 141. Water pipe; 15. Coating membrane; 151. Coating cavity; 16. Support member; 17. Movable member; 18. Sound-transmitting film;

[0040] 20. Ultrasonic generating device; 21. Driving assembly; 22. Generating assembly; 221. Piezoelectric chip; 2211. Partitioning groove; 2212. Piezoelectric chip; 23. Cable;

[0041] 30. Imaging device;

[0042] 40. Temperature sensor. Modes for Carrying Out the Invention

[0043] In order to make the purpose, technical solutions and advantages of this application more clearly understood, the following further describes this application in detail with reference to the accompanying drawings, i.e., embodiments. It should be understood that the specific embodiments described herein are only used to explain this application and are not intended to limit this application.

[0044] It should be noted that when a component is referred to as being "fixed on" or "disposed on" another component, it may be directly or indirectly on the other component. When a component is referred to as being "connected to" another component, it may be directly or indirectly connected to the other component. The terms "upper", "lower", "left", "right", etc. indicate orientations or positional relationships based on the orientations or positional relationships shown in the accompanying drawings. They are only for the convenience of description and do not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation. Therefore, they cannot be understood as limitations on the patent. The terms "first" and "second" are only used for the convenience of description and cannot be understood as indicating or implying relative importance or implicitly indicating the number of technical features. "Multiple" means two or more, unless otherwise clearly and specifically defined.

[0045] It should also be noted that, in the embodiments of the present application, the same figure mark represents the same component or the same part. For the same parts in the embodiments of the present application, the figure may only mark one of the parts or components as an example. It should be understood that the figure mark also applies to other identical parts or components.

[0046] Hypertension is the most common chronic disease and a major risk factor for cardiovascular and cerebrovascular diseases. It can easily lead to stroke, myocardial infarction, heart failure, and chronic kidney disease, earning it the nickname "the invisible killer" of human health. Overexcitation of the renal sympathetic nerves can elevate blood pressure, posing a high mortality risk and a heavy treatment burden. RDN technology involves interventional therapy (via the femoral or radial artery) to disrupt the renal sympathetic afferent and efferent nerves. This technique can weaken renal and systemic sympathetic nerve activity, thereby lowering blood pressure.

[0047] RDN techniques can be based on radiofrequency ablation, ultrasonic ablation, cryoablation, and chemical ablation, but currently, radiofrequency ablation (rRDN) and ultrasonic ablation (uRDN) are the dominant methods. Radiofrequency ablation involves delivering a catheter with an electrode to the renal artery. The electrode then outputs radiofrequency energy, heating the tissue surrounding the electrode and gradually conducting the radiofrequency current or heat below the renal artery adventitia. Although radiofrequency ablation can reduce the temperature of the electrode and the renal artery endothelium through cold saline perfusion, there is still a risk of intimal damage and renal artery stenosis.

[0048] Ultrasonic energy has advantages such as good penetration and high energy controllability, and has certain technical advantages in the field of RDN. Currently, existing technologies mainly include circular transducers with 360° energy emission and planar transducers with directional energy emission. However, neither the circular nor the planar transducer solution can achieve spatial regulation of the sound field and ultrasonic energy distribution, which can easily lead to the risk of renal artery wall damage and renal artery stenosis, requiring cooling water to cool the renal artery endothelium.

[0049] Based on the above considerations, in order to alleviate the damage that ultrasonic energy may cause to the blood vessel wall, the present application provides an ablation catheter including an ultrasonic generating device, so that the ultrasonic generating device includes a driving component and a generating component, and the ultrasonic waves emitted by the generating component can converge outside the blood vessel wall to form a focus, so that the ultrasonic waves can have greater energy at the focus to ablate the sympathetic nerves at the corresponding position.

[0050] At the location where the ultrasound waves pass through the blood vessel wall, the ultrasound waves have not yet converged at a focal point, so the ultrasound waves are more dispersed and carry lower energy, causing the blood vessel wall to heat up less, thereby alleviating the damage caused by the ultrasound waves to the blood vessel wall.

[0051] Such an ablation catheter can not only ablate the target sympathetic nerves outside the blood vessels, but also alleviate the damage of ultrasound to the blood vessel wall. It has a simple structure, reduces the difficulty of operation, and also reduces the cost of the ablation catheter.

[0052] In addition to being used to ablate renal sympathetic nerves, the ablation catheter provided in the embodiments of the present application can also be used to ablate tissues in other parts of the body, such as prostate hyperplasia tissue, etc. For the sake of convenience, the following embodiments will use the ablation catheter provided in some embodiments of the present application to ablate renal sympathetic nerves as an example.

[0053] In the first aspect, some embodiments of the present application provide an ablation catheter 100, referring to Figures 1 to 4, wherein Figure 1 is a partial stereoscopic schematic diagram of the ablation catheter 100 provided by some embodiments of the present application, Figure 2 is a partial stereoscopic schematic diagram of the ablation catheter 100 provided by other embodiments of the present application, Figure 3 is a cross-sectional schematic diagram of the ablation catheter 100 shown in Figure 1, and Figure 4 is a partial enlarged schematic diagram of point A in Figure 3; because the length of the ablation catheter 100 is usually long, Figures 1 and 2 only show part of the structure of the end of the ablation catheter 100.

[0054] The ablation catheter 100 includes a catheter assembly 10 and an ultrasonic generating device 20, wherein the ultrasonic generating device 20 is arranged in the catheter assembly 10, and the ultrasonic generating device 20 includes a driving assembly 21 and a generating assembly 22 connected to the driving assembly 21, the driving assembly 21 is used to drive the generating assembly 22 to vibrate, and the generating assembly 22 is used to emit ultrasonic waves and converge the ultrasonic waves at a focus, and the focus is set outside the catheter assembly 10.

[0055] The catheter assembly 10 refers to a structure or structural assembly for carrying the ultrasonic generator 20 and other devices. The catheter assembly 10 can enter the patient's blood vessels and move along the patient's blood vessels. The ultrasonic generator 20 and other devices are housed in the catheter assembly 10 and can move to the target position along one end of the catheter assembly 10; the catheter assembly 10 may include one or more tubular structures; the material of the catheter assembly 10 may be polytetrafluoroethylene, silicone rubber, polyurethane or other materials; the shape of the catheter assembly 10 may be cylindrical, prismatic or other shapes.

[0056] The ultrasonic generating device 20 refers to a structure or a combination of structures that can emit ultrasonic waves. The ultrasonic waves emitted by the ultrasonic generating device 20 can penetrate the blood vessel wall and ablate the target sympathetic nerves; the ultrasonic generating device 20 may include a transducer, various circuit boards or other structures and devices.

[0057] The driving component 21 refers to a structure or a combination of structures in the ultrasonic generating device 20 for driving the generating component 22 to vibrate. The driving component 21 may include various circuit boards such as an amplifying circuit board. The driving component 21 may also include a matching layer, a backing and other structures. The driving component 21 is used to drive the vibration of the generating component 22. For example, the driving component 21 can receive and process electrical signals and send the processed electrical signals to the generating component 22.

[0058] The generating component 22 refers to a structure or structural combination in the ultrasonic generating device 20 that can generate ultrasonic waves; the generating component 22 may include only one device that can vibrate and generate ultrasonic waves, or the generating component 22 may include multiple devices that can vibrate and generate ultrasonic waves; the material of the generating component 22 may be barium titanate ceramic, lead titanate ceramic or other materials; the generating component 22 can receive the electrical signal sent by the driving component 21, and generate mechanical vibration according to the received electrical signal, thereby generating ultrasonic waves.

[0059] The ultrasonic waves generated by the generating component 22 can converge at the focus, so that the ultrasonic waves can generate greater energy at the focus, and use the energy to ablate the sympathetic nerves at the corresponding position. Specifically, the generating component 22 can be provided with a device of a specific shape or multiple devices to converge the ultrasonic waves generated by the generating component 22 at the focus. In some embodiments, the generating component 22 may include a device of a specific shape, in which case the specific shape of the piezoelectric piece 221 may be an arc, a U-shape, or other shapes, so that the ultrasonic waves generated by the generating component 22 can converge at the focus; in other embodiments, the generating component 22 may also include multiple devices, and the multiple devices may also be arranged along an arc, a U-shape, an L-shape, or other shaped tracks, so that the ultrasonic waves generated by the generating component 22 can converge at the focus; it can be understood that the generating component 22 may also adopt other structures to converge the ultrasonic waves at the focus, and is not limited to the aforementioned method.

[0060] Before the ultrasonic waves generated by the generating component 22 converge at the focus, the ultrasonic waves are relatively dispersed and carry less energy. Specifically, the closer the ultrasonic waves are to the ultrasonic generating device 20, the less energy they carry. The inner diameter of the blood vessel is usually smaller, so when the ultrasonic waves pass through the blood vessel wall, they are closer to the ultrasonic generating device 20, the energy they carry is smaller, and the damage to the blood vessel wall by the ultrasonic waves is also smaller.

[0061] In this embodiment, the ultrasonic generating device 20 includes a driving component 21 and a generating component 22, and the ultrasonic waves emitted by the generating component 22 can converge outside the blood vessel wall to form a focus, so that the ultrasonic waves can have greater energy at the focus to ablate the sympathetic nerves at the corresponding position; and at the position where the ultrasonic waves pass through the blood vessel wall, the ultrasonic waves are more dispersed and carry lower energy, so that the blood vessel wall generates less heat, thereby alleviating the damage of the ultrasonic waves to the blood vessel wall.

[0062] In some embodiments, the ultrasonic generating device 20 is an ultrasonic transducer. In this case, the driving component 21 may include a flexible circuit board, a matching layer, a backing and other structures, and the generating component 22 may include a structure formed by piezoelectric material.

[0063] In some embodiments, the ultrasonic generating device 20 is connected to an external device through a cable 23, one end of the cable 23 is connected to the driving component 21 or the generating component 22, and the other end of the cable 23 can pass through the catheter component 10 and extend to the outside world, so that the external device can send an electrical signal to the ultrasonic generating device 20 through the cable 23.

[0064] According to some embodiments of the present application, refer to Figures 3, 4, 6, 7, and 9, wherein Figure 3 is a cross-sectional schematic diagram of the ablation catheter 100 provided in some embodiments of the present application, Figure 4 is a partially enlarged schematic diagram of point A in Figure 3, Figure 6 is a cross-sectional schematic diagram of the ablation catheter 100 provided in other embodiments of the present application, Figure 7 is a partially enlarged schematic diagram of point C in Figure 6, and Figure 9 is a three-dimensional schematic diagram of the ultrasonic generating device 20 in the ablation catheter 100 provided in some embodiments of the present application.

[0065] The generating assembly 22 includes an arc-shaped piezoelectric piece 221 , and the center and focus of the piezoelectric piece 221 are located on the same side of the catheter assembly 10 .

[0066] The piezoelectric sheet 221 refers to a structure that can receive electrical signals and generate mechanical vibrations. For example, the piezoelectric sheet 221 can receive electrical signals sent by the driving component 21 and generate internal stress inside the material, thereby causing the material to vibrate and form ultrasonic waves. The material of the piezoelectric sheet 221 can be barium titanate ceramics, lead titanate ceramics or other materials.

[0067] The arc-shaped piezoelectric piece 221 means that the shape of the piezoelectric piece 221 is arc-shaped. Specifically, the shape of the piezoelectric piece 221 can be a part of the side wall of a thin-walled cylindrical structure, a part of the wall surface of a thin-walled spherical structure, or other arc-shaped structures.

[0068] The center and the focus of the piezoelectric piece 221 are located on the same side of the catheter assembly 10 , that is, the piezoelectric piece 221 protrudes in a direction away from the focus.

[0069] When the arc-shaped piezoelectric piece 221 receives an electrical signal and vibrates, the generated ultrasonic waves can converge near the center of the circle or sphere of the arc-shaped piezoelectric piece 221, so that the ultrasonic waves can achieve the effect of converging at a focal point.

[0070] In this embodiment, the generating component 22 includes an arc-shaped piezoelectric piece 221, which emits focusable ultrasonic waves so that the ultrasonic waves have higher energy at the focus, thereby achieving the effect of ablating the sympathetic nerves at the corresponding position.

[0071] In some embodiments, the radius of the piezoelectric sheet 221 ranges from 6 mm to 15 mm, wherein the radius of the piezoelectric sheet 221 can be 6 mm, 7 mm, 8 mm, 9 mm, 10 mm, 11 mm, 12 mm, 13 mm, 14 mm, 15 mm or other values.

[0072] Since the ultrasonic waves generated by the piezoelectric piece 221 can converge near the center of the circle or sphere of the arc-shaped piezoelectric piece 221 , the position of the ultrasonic focus can be adjusted by adjusting the radius of the piezoelectric piece 221 .

[0073] Because the sympathetic nerves are mainly located in the fatty tissue outside the adventitia of the renal artery, and the depth range of the sympathetic nerves is 2 to 7 millimeters (mm) from the renal artery endothelium, the radius range of the piezoelectric plate 221 is set to 6 mm to 15 mm so that the focus can be within the range of 2 to 7 mm from the renal artery endothelium, so that the ultrasound can ablate the sympathetic nerves at the focus.

[0074] This embodiment further limits the radius range of the piezoelectric sheet 221 to limit the position range of the focus by limiting the radius range of the piezoelectric sheet 221, so that the ultrasound can ablate the sympathetic nerves at the focus and reduce damage to the blood vessel wall during the process of passing through the blood vessel wall.

[0075] In some embodiments, referring to FIG. 10 , FIG. 10 shows a specific structure of a piezoelectric sheet 221 provided in some embodiments of the present application.

[0076] At least one partition groove 2211 is formed on the piezoelectric sheet 221 . The partition groove 2211 can separate the piezoelectric sheet 221 into at least two piezoelectric sheets 2212 . The piezoelectric sheets 2212 can rotate relative to the driving assembly 21 .

[0077] The partition groove 2211 refers to a through groove opened on the piezoelectric sheet 221. The partition groove 2211 can cut the piezoelectric sheet 221 and form two piezoelectric sheets 2212. As the number of partition grooves 2211 increases, the number of piezoelectric sheets 2212 will also increase; the partition groove 2211 can extend along the length direction of the piezoelectric sheet 221, or extend along the width direction of the piezoelectric sheet 221. The partition groove 2211 can also extend along other directions, and multiple partition grooves 2211 can also extend along different directions.

[0078] The number of piezoelectric sheets 2212 can be two or more. In some embodiments, the number of piezoelectric sheets 2212 is an odd number. Furthermore, in the radial direction of the catheter assembly 10, the piezoelectric sheets 2212 have an odd number of columns, and the piezoelectric sheets 2212 in each column are arranged along the length of the catheter assembly 10.

[0079] It can be understood that the multiple piezoelectric sheets 2212 formed by the partition groove 2211 are all on the same curved surface, which can be a part of a cylindrical side wall, a part of a spherical wall, or other curved surfaces; this setting enables the ultrasonic waves formed by the multiple piezoelectric sheets 2212 to converge at the center of the circle or the center of the sphere of the curved surface.

[0080] The piezoelectric chip 2212 can rotate relative to the driving component 21. As the piezoelectric chip 2212 rotates, the shape of the arc surface will also change, and the position of the center of the circle or the center of the sphere of the arc surface will also change. That is, the rotation of the piezoelectric chip 2212 can adjust the position of the focus to facilitate the ablation of sympathetic nerves in different positions and meet different ablation needs.

[0081] The rotation of the piezoelectric chip 2212 relative to the driving component 21 may have only one rotation direction, or may have two or more rotation directions; the rotation of the piezoelectric chip 2212 may be driven by a micro-driving device, or may be driven by other structures.

[0082] In this embodiment, the piezoelectric sheet 221 is separated into a plurality of piezoelectric sheets 2212 by a partition groove 2211, and each piezoelectric sheet 2212 is able to move relative to the driving component 21, so that each piezoelectric sheet 2212 can adjust its direction and angle, and multiple piezoelectric sheets 2212 can form a phased array structure, so that the staff can adjust the position of the focus as needed, thereby improving the compatibility of the ablation catheter 100.

[0083] In some embodiments, the partition grooves 2211 may be filled with insulating and absorbing materials to reduce the mutual influence between the piezoelectric chips 2212 . The insulating and absorbing materials may be epoxy resin, silicone or other materials.

[0084] According to some embodiments of the present application, the generating component 22 includes a first state and a second state, the sound power of the ultrasonic wave emitted by the generating component 22 in the first state is greater than the sound power of the ultrasonic wave emitted by the generating component 22 in the second state, and the sound power of the ultrasonic wave emitted by the generating component 22 in the second state is less than or equal to 10%. For example, the sound power of the ultrasonic wave emitted by the generating component 22 in the second state can be 10%, 7%, 5%, 4%, 3%, 2%, 1% or other values.

[0085] Sound power refers to the energy radiated outward by a sound source per unit time. The greater the sound power, the greater the energy transmitted by the ultrasonic wave per unit time.

[0086] The second state of the generating component 22 is used to map the sympathetic nerves. Because parasympathetic nerves usually exist near the sympathetic nerves, and ablation of the parasympathetic nerves will have a negative impact on blood pressure control, the second state is set to distinguish between the sympathetic nerves and the parasympathetic nerves.

[0087] The first state of the generating component 22 is used to ablate the sympathetic nerves at the focus, so the acoustic power of the ultrasonic waves emitted by the generating component 22 in the first state is greater than the acoustic power of the ultrasonic waves emitted by the generating component 22 in the second state, so that the ultrasonic waves emitted by the generating component 22 in the first state can carry sufficient energy to ablate the sympathetic nerves.

[0088] Specifically, the acoustic power of the ultrasonic wave emitted by the generating component 22 in the second state is called low power. The energy carried by low-power ultrasonic waves is small and will not cause tissue damage, but low-power ultrasonic waves can cause changes in the permeability of nerve cells and ion channels, thereby forming a nerve stimulation response and causing changes in blood pressure. The stimulation responses produced by the sympathetic nerves and parasympathetic nerves have different effects on blood pressure, so staff can distinguish between the sympathetic nerves and parasympathetic nerves through changes in blood pressure to achieve the effect of mapping.

[0089] Low-power ultrasound waves do not damage sympathetic nerves, but they can alter pericardial permeability, ion channels, and other parameters, leading to nerve stimulation responses. This stimulation response allows personnel to identify and determine the target nerve for ablation. Therefore, this embodiment provides two acoustic power ranges for ultrasound waves, enabling the ablation catheter 100 to both ablate and identify nerves.

[0090] According to some embodiments of the present application, referring to FIG. 10 , FIG. 10 shows a specific structure of a piezoelectric sheet 221 provided in some embodiments of the present application.

[0091] The ablation catheter 100 further includes an imaging device 30 , which is disposed in the catheter assembly 10 and on one side of the ultrasound generating device 20 .

[0092] The imaging device 30 refers to a device that can enter the blood vessel along with the catheter assembly 10 and collect images near the blood vessel. The imaging device 30 can be an imaging ultrasound transducer, an optical coherence tomography (OCT) optical device, or other imaging devices.

[0093] The imaging device 30 can be connected to an external device for communication to send the collected images to the external device, so that the staff can determine the position of the catheter assembly 10, the position of the part to be ablated and other information based on the image, thereby facilitating the staff to better perform the ablation operation.

[0094] In some embodiments, the imaging device 30 is disposed on the side of the generating component 22 away from the driving component 21, and the imaging device 30 is disposed in the direction in which the ultrasonic wave is emitted so that the ultrasonic wave can reach the position of the imaging device 30 to obtain image information.

[0095] In this embodiment, an imaging device 30 is provided next to the ultrasound generating device 20 so that the staff can obtain tissue images at corresponding positions, thereby facilitating the staff to perform ablation operations.

[0096] According to some embodiments of the present application, refer to Figures 3, 5, 6, and 8, wherein Figure 3 is a cross-sectional schematic diagram of the ablation catheter 100 provided in some embodiments of the present application, Figure 5 is a cross-sectional schematic diagram at BB in Figure 3 and shows the internal structure of the catheter assembly 10, Figure 6 is a cross-sectional schematic diagram of the ablation catheter 100 provided in other embodiments of Figure 2, and Figure 8 is a cross-sectional schematic diagram at DD in Figure 6 and shows the internal structure of the catheter assembly 10.

[0097] The catheter assembly 10 includes an outer tube 11 and a rotating member 12 arranged in the outer tube 11. The outer tube 11 is provided with a accommodating cavity 111, and the ultrasonic generating device 20 is accommodated in the accommodating cavity 111; one end of the rotating member 12 extends into the accommodating cavity 111 and is connected to the ultrasonic generating device 20. The rotating member 12 can bend with the outer tube 11, and the rotating member 12 can rotate relative to the outer tube 11 and drive the ultrasonic generating device 20 to rotate.

[0098] The outer tube 11 refers to a structure or a combination of structures used to carry the rotating part 12, the ultrasonic generating device 20, etc.; the material of the outer tube 11 can be polytetrafluoroethylene, silicone rubber, polyurethane or other materials; the shape of the outer tube 11 can be cylindrical, prismatic or other shapes.

[0099] The accommodating cavity 111 refers to the space formed in the outer tube 11; the accommodating cavity 111 may only refer to the space set in the outer tube 11, or it may be the space surrounded by the structure in the outer tube 11; the accommodating cavity 111 is mainly used to accommodate the ultrasonic generating device 20, and the accommodating cavity 111 may also accommodate the imaging device 30 or other structures and devices.

[0100] The rotating member 12 refers to a structure that can be bent and still rotate after bending. The rotating member 12 has good torque transmission performance and good flexibility. The rotating member 12 can be a torque spring tube or other structures that can be bent and still rotate after bending.

[0101] The ultrasonic generating device 20 is accommodated in the accommodating cavity 111 , and the outer tube 11 moving in the blood vessel can drive the ultrasonic generating device 20 to move synchronously and move to the target position.

[0102] The rotating member 12 is accommodated in the outer tube 11. The rotating member 12 can be coaxially arranged with the outer tube 11, or eccentrically and non-coaxially arranged. The outer tube 11 moves in the blood vessel and can drive the rotating member 12 to move synchronously; one end of the rotating member 12 can extend into the accommodating cavity 111 and be connected to the ultrasonic generating device 20, so that the rotating member 12 can drive the ultrasonic generating device 20 to rotate in the accommodating cavity 111; it can be understood that the other end of the rotating member 12 away from the ultrasonic generating device 20 can extend to the outside world, so that the staff can drive the rotating member 12 to rotate through equipment or manually.

[0103] The rotating member 12 can bend synchronously with the outer tube 11. At the same time, after the outer tube 11 bends, the rotating member 12 can still drive the ultrasonic generating device 20 to rotate in the accommodating cavity 111. Because the blood vessels of patients with vascular diseases are usually more tortuous, the ultrasonic generating device 20 usually undergoes multiple bends before reaching the target position. Therefore, using the rotating member 12 to drive the ultrasonic generating device 20 can better drive the ultrasonic generating device 20 to rotate in the accommodating cavity 111.

[0104] The rotating part 12 drives the ultrasonic generating device 20 to rotate, so that the ablation catheter 100 can better adjust the ablation position according to the actual situation of the patient, thereby increasing the applicability of the ablation catheter 100; and because the renal artery sympathetic nerves are mainly wrapped around the renal artery in a reticular structure, the rotating part 12 drives the ultrasonic generating device 20 to rotate, so that the focus of the ultrasonic wave can also rotate roughly around the blood vessel as the axis, and form an annular ablation area surrounding the blood vessel, so as to facilitate the ablation of the sympathetic nerves around the blood vessel, thereby improving the efficiency of ablation and reducing the situation where the ablation catheter 100 reciprocates in and out of the blood vessel.

[0105] In this embodiment, the catheter assembly 10 includes a rotating part 12, and the rotating part 12 drives the ultrasonic generating device 20 to rotate. The rotating part 12 can bend along with the outer tube 11 when the outer tube 11 bends, and the rotating part 12 can also drive the ultrasonic generating device 20 to rotate when the outer tube 11 bends, so that the focus of the ultrasonic wave generated by the ultrasonic generating device 20 can move around the blood vessel, thereby increasing the ablation area and better adapting to the distribution of the renal artery sympathetic nerves.

[0106] In some embodiments, an end piece 113 is provided at one end of the outer tube 11. The end piece 113 can seal the end of the outer tube 11, thereby reducing the occurrence of liquid or other substances in the outer tube 11 or the accommodating cavity 111 entering the blood vessel, and can also reduce the occurrence of blood vessel or external substances entering the outer tube 11.

[0107] The end piece 113 also has the function of guiding the ablation catheter 100 to move in the blood vessel, so the end of the end piece 113 away from the outer tube 11 can be set to a pointed tip to reduce the resistance of the ablation catheter 100 to the movement in the blood vessel; the end of the end piece 113 away from the outer tube 11 can also be set to a round head, which can reduce the resistance of the ablation catheter 100 to the movement in the blood vessel while reducing the damage of the end piece 113 to the blood vessel wall.

[0108] In some embodiments, the catheter assembly 10 further includes a liquid inlet channel 13 and a liquid discharge channel 14 provided on the outer tube 11 , and one end of the liquid inlet channel 13 and the liquid discharge channel 14 are both connected to the accommodating cavity 111 .

[0109] The liquid inlet channel 13 and the liquid discharge channel 14 both refer to a channel structure or a combination of structures for transporting liquid; one end of the liquid inlet channel 13 and the liquid discharge channel 14 are both connected to the accommodating chamber 111, that is, the liquid inlet channel 13 is used to transport liquid into the accommodating chamber 111, and the liquid discharge channel 14 is used to discharge the liquid in the accommodating chamber 111, thereby forming a circulating liquid flow to facilitate reducing the temperature in the accommodating chamber 111.

[0110] The liquid flowing through the liquid inlet channel 13 and the liquid outlet channel 14 is used to reduce the temperature in the accommodation chamber 111 . The liquid may include water, ethylene glycol or other materials.

[0111] Because the ultrasonic generating device 20 generates heat during operation, and the ultrasonic wave itself also carries heat, in order to reduce the damage to the blood vessel wall caused by excessive heat, a liquid inlet channel 13 and a liquid discharge channel 14 are provided to form a circulating liquid flow flowing through the accommodating cavity 111 to reduce the temperature inside the accommodating cavity 111, thereby reducing possible damage to the blood vessel wall caused by high temperature.

[0112] It can be understood that the ends of the liquid inlet channel 13 and the liquid discharge channel 14 away from the accommodating chamber 111 can be connected to the outside world, so that external equipment can transport liquid to the accommodating chamber 111 through the liquid inlet channel 13, and the liquid in the accommodating chamber 111 can be discharged to the outside world through the liquid discharge channel 14.

[0113] The liquid inlet channel 13 and the liquid discharge channel 14 can be arranged inside the outer tube 11 or outside the outer tube 11; in some embodiments, a water inlet pipe and a water outlet pipe are respectively provided outside the outer tube 11, and in this case, the liquid inlet channel 13 and the liquid discharge channel 14 are respectively formed in the water inlet pipe and the water outlet pipe; in other embodiments, a water inlet pipe and a water outlet pipe are respectively provided inside the outer tube 11, and in this case, the liquid inlet channel 13 and the liquid discharge channel 14 are respectively formed in the water inlet pipe and the water outlet pipe; in some other embodiments, a partition structure is provided inside the outer tube 11, so that the partition structure cooperates with the tube wall of the outer tube 11 to form the liquid inlet channel 13 and the liquid discharge channel 14.

[0114] In some embodiments, a water pipe 141 is provided in the outer tube 11 , a liquid inlet channel 13 is formed between the outer wall of the water pipe 141 and the inner wall of the outer tube 11 , and a liquid outlet channel 14 is formed inside the inner wall of the water pipe 141 .

[0115] The cable 23 can be passed through the water pipe 141, or passed through the outer wall of the water pipe 141 and the inner wall of the outer tube 11; the rotating member 12 can be coaxially arranged with the water pipe 141 and sleeved on the outside of the water pipe 141, or the rotating member 12 can be coaxially arranged with the water pipe 141 and passed through the water pipe 141, or the rotating member 12 can not be coaxially arranged with the water pipe 141.

[0116] In this embodiment, a liquid inlet channel 13 and a liquid discharge channel 14 are provided in the catheter assembly 10, and the liquid inlet channel 13 and the liquid discharge channel 14 are connected to the accommodating chamber 111, thereby forming a circulating water circuit in the catheter assembly 10. The ultrasonic generating device 20 is cooled by the circulating water, thereby reducing damage to the blood vessel wall that may be caused by excessive temperature of the ultrasonic generating device 20.

[0117] In some embodiments, the ablation catheter 100 further includes a temperature sensor 40 , which is disposed on one side of the ultrasound generating device 20 .

[0118] The temperature sensor 40 refers to a device used to detect the temperature near the ultrasonic generating device 20. The temperature sensor 40 can be connected to an external device for communication so as to send the monitored real-time temperature information to the outside world. The staff can perform operations based on the real-time temperature information, such as shutting down when the real-time temperature is high, increasing the liquid flow, and increasing the liquid flow rate.

[0119] The temperature sensor 40 can be connected to external equipment through a signal line passing through the outer tube 11, or can be connected to external equipment wirelessly, or communicated with in other ways; in some embodiments, the temperature sensor 40 is a cable-shaped thermocouple temperature sensor that passes through the outer tube 11 and extends at one end to the side of the ultrasonic generating device 20.

[0120] In this embodiment, a temperature sensor 40 is provided on one side of the ultrasonic generating device 20 to facilitate staff to monitor the temperature of the ultrasonic generating device 20 , thereby reducing possible damage to the blood vessel wall caused by excessive temperature.

[0121] In some embodiments, the ultrasonic generating device 20 may also include a base or a housing for providing a fixed foundation for the driving component 21, the generating component 22 and the cable 23. In this case, one end of the temperature sensor 40 can be placed in the base or the housing and located close to the piezoelectric piece 221 to better obtain real-time temperature information near the piezoelectric piece 221.

[0122] According to some embodiments of the present application, refer to Figures 3 and 4, where Figure 3 is a cross-sectional schematic diagram of the ablation catheter 100 provided in some embodiments of the present application, and Figure 4 is an enlarged view of point A in Figure 3 and shows the specific structure inside the covering cavity 151.

[0123] The catheter assembly 10 also includes a covering film 15 arranged around the outer tube 11. The covering film 15 forms a covering cavity 151 outside the outer tube 11. The covering cavity 151 is connected to the accommodating cavity 111. The covering film 15 can move toward or away from the accommodating cavity 111.

[0124] The coating film 15 refers to a thin film structure or structural component arranged around the outer tube 11. The coating film 15 can form a coating cavity 151 outside the outer tube 11. The coating cavity 151 is a sealed structure and cannot communicate with the outside world.

[0125] The covering cavity 151 is connected with the accommodating cavity 111, that is, the covering cavity 151 covers the accommodating cavity 111 outside the outer tube 11; in some embodiments, the outer tube 11 is divided into the accommodating cavity 111 and is divided into two ends and respectively referred to as the front section and the rear section, and the space between the front section and the rear section is the accommodating cavity 111. At this time, the accommodating cavity 111 is an open space set between the front section and the rear section, and the covering cavity 151 covers and is connected with the accommodating cavity 111, that is, the accommodating cavity 111 is in the covering cavity 151 and is part of the space of the covering cavity 151; in other embodiments, a through hole or channel is provided on the outer tube 11 to connect the accommodating cavity 111 and the covering cavity 151 through the through hole or channel.

[0126] Because the covering cavity 151 covers the accommodating cavity 111, and the ultrasonic generating device 20 is accommodated in the accommodating cavity 111, the covering film 15 is a thin film structure. The purpose is to reduce the negative impact of the covering film 15 on the ultrasonic wave, such as reducing the energy attenuation of the ultrasonic wave in the process of passing through the covering film 15; the material of the covering film 15 can be silicone rubber, polyurethane (PU), polytetrafluoroethylene (PIFE), polyamide (PA), polyethylene terephthalate (PET), etc.; the thickness of the covering film 15 should be relatively thin to reduce the negative impact on the ultrasonic wave, and it should also have a certain strength. For example, the thickness of the covering film 15 can be 0.01 mm, 0.02 mm, 0.03 mm or other thicknesses.

[0127] When the outer tube 11 drives the ultrasonic generator 20 into the patient's blood vessel and reaches the target position, the liquid can enter the accommodating cavity 111 through the liquid inlet channel 13 and enter the coating cavity 151. At this time, the drainage channel 14 can be closed first. As the liquid enters, the coating cavity 151 can gradually expand. At this time, the coating film 15 moves away from the accommodating cavity 111 until it abuts against the blood vessel wall, so as to achieve the effect of fixing the outer tube 11, thereby fixing the position of the ultrasonic generator 20 and reducing the shaking that may occur during use of the ultrasonic generator 20; when ablation After completion, liquid no longer needs to be transported into the accommodating cavity 111 through the liquid inlet channel 13, and the liquid in the coating cavity 151 can be discharged through the liquid discharge channel 14. At this time, the coating film 15 gradually moves toward the accommodating cavity 111 and separates from the blood vessel wall as the liquid decreases, so as to facilitate the removal of the outer tube 11 and reduce the negative impact that may be caused by the removal of the outer tube 11; in some embodiments, when there is no liquid in the coating cavity 151, the coating film 15 can be in contact with the outer tube 11 to better reduce the negative impact that may be caused by the removal of the outer tube 11.

[0128] In this embodiment, a covering film 15 is provided on the outside of the catheter and a covering cavity 151 is formed by the covering film 15. At the same time, the covering cavity 151 is connected to the accommodating cavity 111, so that the water flow can enter the covering cavity 151 after entering the accommodating cavity 111. The covering cavity 151 can gradually expand as the water flow is filled, and the covering film 15 can move away from the accommodating cavity 111 and abut against the blood vessel wall, thereby playing a role in fixing the catheter assembly 10.

[0129] According to some embodiments of the present application, refer to Figures 2, 6, and 7, where Figure 2 is a partial three-dimensional schematic diagram of the ablation catheter 100 provided in some embodiments of the present application, Figure 6 is a cross-sectional schematic diagram of the ablation catheter 100 in Figure 2, and Figure 7 is an enlarged view of point C in Figure 6 and shows the specific structure inside the covering cavity 151.

[0130] The catheter assembly 10 further includes a support member 16 and a movable member 17 disposed outside the outer tube 11 , wherein one end of the support member 16 is connected to the outer tube 11 , and the other end of the support member 16 is connected to the movable member 17 ;

[0131] The movable member 17 is movably connected to the outer tube 11 . The movable member 17 can move relative to the outer tube 11 along the axial direction of the outer tube 11 and can drive the support member 16 to deform in a direction away from or close to the outer tube 11 .

[0132] The support member 16 refers to a support structure or a combination of structures provided outside the outer tube 11 ; the shape of the support member 16 may be a strip, a sheet or other shapes; the material of the support member 16 may be metal, plastic, a composite material or other materials.

[0133] The movable member 17 is a structure or combination of structures that can move axially along the outer tube 11. The movable member 17 can be cylindrical, sheet-like, strip-like, or other shapes. The movable member 17 can be made of metal, plastic, composite materials, or other materials. In some embodiments, the movable member 17 is a sleeve coaxially mounted on the outer tube 11 and is capable of bending and deformation.

[0134] The support member 16 can fit into the outer tube 11 and can also be deformed in the direction away from the outer tube 11. When the support member 16 is deformed in the direction away from the outer tube 11, it can abut against the blood vessel wall to fix the position of the outer tube 11 and further fix the ultrasonic generating device 20.

[0135] One end of the support member 16 is connected to the outer wall of the outer tube 11, and the other end of the support member 16 is connected to the movable member 17. When the movable member 17 moves along the axial direction of the outer tube 11 toward the support member 16, the middle part of the support member 16 is compressed and deformed, and deformed in the direction away from the outer tube 11; when the movable member 17 moves along the axial direction of the outer tube 11 toward the direction away from the support member 16, the middle part of the support member 16 is tensile and deformed, and deformed in the direction close to the outer tube 11 to touch the outer wall of the outer tube 11.

[0136] In this embodiment, a support member 16 and a movable member 17 are provided on the catheter. The support member 16 can be deformed in a direction away from the outer tube 11 and abut against the blood vessel wall as the movable member 17 moves, thereby fixing the position of the outer tube 11; the support member 16 can also be deformed in a direction close to the outer tube 11 to facilitate the catheter assembly 10 to enter the blood vessel and move within the blood vessel.

[0137] In some embodiments, the shape of the support member 16 can be set to be an arc convex in a direction away from the outer tube 11 , so that the support member 16 can be deformed in a direction away from the outer tube 11 .

[0138] In some embodiments, the support member 16 is a sheet-like structure, and there are multiple support members 16. The multiple support members 16 are evenly spaced around the outer tube 11. When the movable member 17 moves toward the direction close to the support member 16 and deforms the support member 16, the multiple support members 16 are deformed and form a ball-cage-like structure.

[0139] In some embodiments, in order to reduce the negative impact of the support member 16 on the ultrasonic waves generated by the ultrasonic generating device 20 , the support member 16 and the ultrasonic generating device 20 are staggered along the axial direction of the outer tube 11 .

[0140] According to some embodiments of the application, refer to Figures 6 and 7, where Figure 6 is a cross-sectional schematic diagram of the ablation catheter 100 provided in some embodiments of the present application, and Figure 7 is an enlarged view of point C in Figure 6 and shows the specific structure inside the covering cavity 151.

[0141] The outer tube 11 is provided with an opening 112 communicating with the accommodating cavity 111 , and the opening 112 is opposite to the ultrasonic generating device 20 ; a sound-transmitting film 18 is provided on the opening 112 , and the sound-transmitting film 18 is used to seal the opening 112 and allow ultrasonic waves to pass through.

[0142] An opening 112 is provided on the outer tube 11 , and the accommodating chamber 111 can be connected to the outside world through the opening 112 . An acoustically transparent film 18 is provided on the outer tube 11 and seals the opening 112 , so that the liquid in the accommodating chamber 111 cannot flow out of the outer tube 11 through the opening 112 . At the same time, ultrasonic waves can pass through the acoustically transparent film 18 , and substances in the blood vessels or the outside world cannot enter the accommodating chamber 111 through the acoustically transparent film 18 .

[0143] Compared with ultrasonic waves passing through the wall of the outer tube 11 and converging toward the target position, the sound-transmitting film 18 can reduce the negative impact on ultrasonic waves, for example, it can reduce the attenuation of ultrasonic energy during transmission; the thickness of the sound-transmitting film 18 should be relatively thin to reduce the negative impact on ultrasonic waves, and it should also have a certain strength. For example, the material of the sound-transmitting film 18 can be silicone rubber, PU, ​​PIFE, PA, PET, etc., and the thickness of the sound-transmitting film 18 can be 0.01mm, 0.02mm, 0.03mm or other thicknesses.

[0144] Based on the function of the sound-transmitting membrane 18 , the opening 112 is opposite to the ultrasonic generator 20 , which enables ultrasonic waves to be transmitted through the sound-transmitting membrane 18 to the target location.

[0145] In this embodiment, an opening 112 is provided on the outer tube 11 opposite to the ultrasonic generating device 20, and a sound-transmitting film 18 is provided on the opening 112 to reduce the influence of the wall of the outer tube 11 on the transmission of ultrasonic waves. At the same time, the sound-transmitting film 18 can also maintain the sealing of the accommodating cavity 111 to prevent water or other impurities from entering the blood vessel.

[0146] According to some embodiments of the present application, the ablation catheter 100 can be used not only to ablate the sympathetic nerves near the renal artery, but also to ablate prostate hyperplasia tissue. This embodiment further illustrates this by taking the ablation of prostate hyperplasia tissue as an example, so that the ablation catheter 100 can not only ablate prostate hyperplasia tissue at the target location, but also reduce damage to the urethral wall.

[0147] Because the ablation catheter 100 can enter through the urethra during the ablation of prostate hyperplasia tissue, the length of the ablation catheter 100 can be shorter, that is, the lengths of the outer tube 11, the rotating member 12, the liquid inlet channel 13, and the liquid discharge channel 14 can all be shorter.

[0148] In addition, during the ablation of benign prostatic hyperplasia tissue, the target location to be ablated may be far away from the urethra, and the farthest location can reach 1 centimeter (cm) from the urethra. At this time, the radius of the piezoelectric piece 221 should be larger, for example, it can be 13mm, 14mm, 15mm or other values, so that the focus can reach a position near 1 cm from the urethra at the farthest, so that the ultrasound can ablate the benign prostatic hyperplasia tissue at the focus.

[0149] Due to the structural characteristics of the urethra, specifically, because the urethra is mostly straight and not curved, the ablation catheter 100 may not have the ability to bend, that is, the outer tube 11 may not have the ability to bend, and the rotating member 12 may also not have the ability to bend and can only rotate within the outer tube.

[0150] Due to the structural characteristics of the urethra, specifically, the width of the external urethral opening and the inner diameter of the urethra are similar, so the ablation catheter 100 does not need to be provided with positioning structures such as the covering film 15 or the support member 16, and the positioning of the ablation catheter 100 can be achieved directly by controlling the outer diameter of the catheter assembly 10.

[0151] In a second aspect, some embodiments of the present application further provide an ablation device, which includes the ablation catheter 100 provided by some embodiments of the first aspect, so that the ablation device can ablate the sympathetic nerves at the target location and reduce damage to the blood vessel wall during the ablation process.

[0152] The ablation device may also include structures or structural combinations such as a handle and a host; for example, the host can provide electrical signals to the ultrasonic generator 20, and the host can also receive signals sent by the temperature sensor 40 and the imaging device 30. The host can also provide liquid to the liquid inlet channel 13 and receive liquid discharged from the liquid discharge channel 14, etc.; for another example, the handle can be held by the staff, and can also control the conduction of the liquid inlet channel 13 and the liquid discharge channel 14, and can also control the displacement of the movable part 17, etc.

[0153] The above embodiments are only used to illustrate the technical solutions of the present application, rather than to limit them. Although the present application has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some of the technical features therein. These modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the various embodiments of the present application, and should all be included in the scope of protection of the present application.

Claims

1. An ablation catheter, characterized in that: include: Catheter components; An ultrasonic generating device is arranged in the catheter assembly, and the ultrasonic generating device includes a driving assembly and a generating assembly connected to the driving assembly, the driving assembly is used to drive the generating assembly to vibrate, the generating assembly is used to emit ultrasonic waves and converge the ultrasonic waves at a focus, and the focus is arranged outside the catheter assembly.

2. The ablation catheter according to claim 1, characterized in that: The generating component comprises an arc-shaped piezoelectric sheet, and the center of the piezoelectric sheet and the focus are arranged on the same side of the catheter component.

3. The ablation catheter according to claim 2, characterized in that: The radius of the piezoelectric sheet is in the range of 6 mm to 15 mm.

4. The ablation catheter according to claim 2, characterized in that: At least one partition groove is provided on the piezoelectric sheet, and the partition groove can separate the piezoelectric sheet into at least two piezoelectric sheets, and the piezoelectric sheets can rotate relative to the driving component.

5. The ablation catheter according to any one of claims 1 to 4, characterized in that: The generating component includes a first state and a second state, and the acoustic power of the ultrasonic wave emitted by the generating component in the second state is less than or equal to 10% of the acoustic power of the ultrasonic wave emitted by the generating component in the first state.

6. The ablation catheter according to any one of claims 1 to 4, characterized in that: The ablation catheter further comprises an imaging device, which is arranged in the catheter assembly and beside the ultrasound generating device.

7. The ablation catheter according to any one of claims 1 to 4, characterized in that: The catheter assembly comprises an outer tube and a rotating member arranged in the outer tube, the outer tube is provided with a receiving cavity, and the ultrasonic generating device is accommodated in the receiving cavity; One end of the rotating member extends into the accommodating cavity and is connected to the ultrasonic generating device. The rotating member can bend along with the outer tube, and the rotating member can rotate relative to the outer tube and drive the ultrasonic generating device to rotate.

8. The ablation catheter according to claim 7, characterized in that: The catheter assembly also includes a liquid inlet channel and a liquid discharge channel arranged on the outer tube, and one end of the liquid inlet channel and the liquid discharge channel are both connected to the accommodating cavity.

9. The ablation catheter according to claim 8, characterized in that: The catheter assembly also includes a covering film arranged around the outer tube, the covering film forms a covering cavity outside the outer tube, the covering cavity is communicated with the accommodating cavity, and the covering film can move toward or away from the accommodating cavity.

10. The ablation catheter according to claim 7, characterized in that: The catheter assembly further includes a support member and a movable member disposed outside the outer tube, one end of the support member being connected to the outer tube, and the other end of the support member being connected to the movable member; The movable member is movably connected to the outer tube, and can move relative to the outer tube along the axial direction of the outer tube, and can drive the supporting member to deform in a direction away from or close to the outer tube.

11. The ablation catheter according to claim 7, characterized in that: The outer tube is provided with an opening connected to the accommodating cavity, and the opening is opposite to the ultrasonic generating device; A sound-transmitting film is provided on the opening, and the sound-transmitting film is used to seal the opening and allow the ultrasonic wave to pass through.

12. The ablation catheter according to any one of claims 1 to 4, characterized in that: The ablation catheter also includes a temperature sensor, which is arranged beside the ultrasound generating device.

13. An ablation device, characterized in that: Comprising the ablation catheter according to any one of claims 1-12.

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