CN118058830A - Laser ablation catheter and laser ablation system - Google Patents

Abstract

The invention discloses a laser ablation catheter and a laser ablation system. The laser ablation catheter comprises an elongated tube structure and an optical fiber bundle, and the optical fiber bundle is arranged in the tube structure; the tube structure comprises an inner layer tube and an outer layer tube, the outer layer tube is sleeved on the periphery of the inner layer tube, and is eccentrically arranged and enclosed with the inner layer tube to form a first optical fiber placement channel, and the inner layer tube is used for a guide wire to pass through; the output end of the optical fiber bundle is positioned at the far end of the tube structure and is provided with an inclined surface which forms an angle with the extending axis of the tube structure; the optical fiber bundle comprises a plurality of first optical fibers, and the core diameter of the first optical fibers is smaller than that of the optical fiber bundle; the plurality of first optical fibers are arranged in the first optical fiber arrangement channel. The far end of the optical fiber bundle releases laser energy, and the inclined surface is arranged at the far end of the optical fiber bundle, so that the optical fiber bundle releases the laser energy towards one direction, the directivity of the released laser energy is stronger, the laser energy is concentrated in a target area needing laser irradiation, the intensity of the laser irradiation energy is greatly increased, and the defect of the laser irradiation energy is avoided.

Description

Laser ablation catheter and laser ablation system

Technical Field

The invention relates to the technical field of medical instruments, in particular to a laser ablation catheter and a laser ablation system.

Background

Currently, laser ablation catheters are used in a variety of procedures, such as excimer laser coronary plaque ablation (Excimer Laser Coronary Atherectomy, ELCA) which primarily delivers ultraviolet pulses to the site of hardening via the laser ablation catheter for the purpose of eliminating the hardened plaque, and renal artery sympatholytic (Renal Denervation, RDN) which irradiates the sympathetic nerve fibers by releasing laser energy to affect, such as destroy, the sympathetic nerve. However, the laser ablation catheter in the related art uniformly releases laser energy in a plurality of directions at the same time, and there is a case where the laser energy in a certain direction is not satisfied.

Disclosure of Invention

The invention aims to provide a laser ablation catheter and a laser ablation system, which aim to solve the technical problem of insufficient laser energy release intensity.

In a first aspect, the present invention provides a laser ablation catheter comprising:

An elongated tube structure comprising an inner tube and an outer tube; the outer layer pipe is sleeved on the periphery of the inner layer pipe, is eccentrically arranged with the inner layer pipe and surrounds the inner layer pipe to form a first optical fiber arranging channel, and the inner layer pipe is used for a guide wire to pass through;

an optical fiber bundle disposed within the tube structure; the output end of the optical fiber bundle is positioned at the far end of the pipe structure and is provided with an inclined surface which forms an angle with the extending axis of the pipe structure;

the optical fiber bundle comprises a plurality of first optical fibers, and the core diameter of the first optical fibers is smaller than that of the optical fiber bundle; the plurality of first optical fibers are arranged in the first optical fiber arrangement channel.

As an implementation mode, the laser ablation catheter further comprises a rotating piece, wherein the rotating piece is connected with the proximal end of the tube structure and used for driving the tube structure and the optical fiber bundle to rotate around the axial direction of the laser ablation catheter in a preset mode, so that the output laser of the optical fiber bundle can irradiate the part to be ablated at an angle of 360 degrees.

As an implementation manner, the rotating member is connected with the proximal end of the tube structure, and is configured to drive the tube structure and the optical fiber bundle to rotate around the axial direction of the laser ablation catheter in a preset manner, so that the output laser of the optical fiber bundle can irradiate the ablation site at an angle of 360 degrees, and specifically includes:

The rotating member is a luer adapter,

The preset mode is to emit laser with the duration of 10 seconds or 15 seconds every 45 degrees or 90 degrees.

As an embodiment, the laser ablation catheter further comprises a balloon assembly, wherein the balloon assembly is in sealing sleeve connection with the distal end of the tube structure along the extending direction of the catheter, so that the inclined surface is arranged in the balloon assembly.

As one embodiment, the balloon assembly comprises a first balloon and/or a second balloon;

the first balloon and/or the second balloon are/is sleeved at the far end of the tube structure in a sealing way, the second balloon is sleeved at the periphery of the first balloon, the inclined surface is arranged in the first balloon, the first balloon is internally filled with first liquid for cooling the output end of the optical fiber bundle, and the second balloon is/is used for filling second liquid for positioning the tube structure at least.

As one embodiment, the output end of the optical fiber bundle is positioned at the distal end of the tube structure and is provided with an inclined surface which forms an angle with the extending axis of the tube structure; the method specifically comprises the following steps: the inclined surface forms an included angle which is larger than or equal to 20 degrees and smaller than or equal to 40 degrees with the axis of the extending direction of the laser ablation catheter.

As one embodiment, the optical fiber bundle further includes a second optical fiber, the second optical fiber being located in the first optical fiber arrangement channel, sharing the optical fiber bundle input end and the optical fiber bundle output end with the first optical fiber, or the second optical fiber being located in the inner tube; the second optical fiber is used for sensing the temperature of the distal end of the optical fiber bundle at the part to be ablated.

As one embodiment, the first optical fiber has a bend radius of less than 10mm; and/or the core diameter of the first optical fiber is less than 200um.

As one embodiment, the second optical fiber has a bend radius of greater than or equal to 10mm and less than or equal to 25mm; and/or the core diameter of the second optical fiber is greater than or equal to 8um and less than or equal to 12um.

As an embodiment, further comprising: the catheter seat is connected with the proximal end of the tube structure, and is provided with a liquid injection port for injecting liquid into the balloon assembly.

In a second aspect, the present invention provides a laser ablation system comprising a laser ablation catheter as described above.

As an embodiment, the laser ablation catheter further comprises a control system at least for controlling the laser with the wavelength of 1064nm to be output to the laser ablation catheter.

According to the laser ablation catheter and the laser ablation system, the inclined surface is arranged at the distal end of the optical fiber bundle, so that the optical fiber bundle releases laser energy towards one direction, namely towards the target area to be irradiated by laser, the directivity of the released laser energy is stronger, the laser energy of the optical fiber bundle is concentrated in the target area, the intensity of the laser energy irradiated to the target area is greatly increased, and the condition of insufficient laser irradiation energy is avoided.

Drawings

In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings that are required in the embodiments or the description of the prior art will be briefly described, and it is obvious that the drawings in the following description are only some embodiments of the present invention, and other drawings may be obtained according to the structures shown in these drawings without inventive effort for a person skilled in the art.

FIG. 1 is a schematic view of a laser ablation catheter according to an embodiment of the present invention;

FIG. 2 is a schematic view of the laser ablation catheter removal catheter hub of FIG. 1;

FIG. 3 is a schematic view of the structure of a distal end of the laser ablation catheter of FIG. 2;

FIG. 4 is a schematic view of another distal end of the laser ablation catheter shown in FIG. 2;

FIG. 5 is a schematic view of yet another distal end of the laser ablation catheter shown in FIG. 2;

Fig. 6 is a schematic view of the structure of the proximal end of the laser ablation catheter shown in fig. 2.

Reference numerals illustrate:

100. A laser ablation catheter; 10. an optical fiber bundle; 11. an inclined surface; 12. a first optical fiber; 13. a second optical fiber; 20. a tube structure; 21. an outer layer tube; 22. an inner layer tube; 23. a first fiber placement channel; 24. a second fiber placement channel; 25. an outer sleeve; 26. a third fiber placement channel; 30. a first balloon; 40. a second balloon; 50. a guide wire; 60. a catheter holder; 70. luer adapter.

The achievement of the objects, functional features and advantages of the present invention will be further described with reference to the accompanying drawings, in conjunction with the embodiments.

Detailed Description

The following description of the embodiments of the present invention will be made clearly and fully with reference to the accompanying drawings, in which it is evident that the embodiments described are only some, but not all embodiments of the invention. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.

It should be noted that all directional indicators (such as up, down, left, right, front, and rear … …) in the embodiments of the present invention are merely used to explain the relative positional relationship between the components, the movement condition, etc. in a specific posture, and if the specific posture is changed, the directional indicators are correspondingly changed.

In the technical field of medical instruments, an orientation close to an operator is generally defined as a proximal end, an orientation far from the operator is defined as a distal end, a radial direction refers to a direction along a diameter or a radius, an axial direction refers to a direction along a central axis, a radial direction and an axial direction are mutually perpendicular, and a circumferential direction refers to a circumferential direction around the central axis. Unless defined otherwise, 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 belongs. The terminology used in the description of the invention herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention.

It will also be understood that when an element is referred to as being "mounted" or "disposed" on another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present.

Furthermore, the description of "first," "second," etc. in this disclosure is for descriptive purposes only and is not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In addition, the technical solutions of the embodiments may be combined with each other, but it is necessary to base that the technical solutions can be realized by those skilled in the art, and when the technical solutions are contradictory or cannot be realized, the combination of the technical solutions should be considered to be absent and not within the scope of protection claimed in the present invention.

As shown in fig. 1 and2, a laser ablation catheter 100 according to an embodiment of the present invention includes an optical fiber bundle 10 and a tube structure 20, where an output end of the optical fiber bundle 10 is located at a distal end of the tube structure 20 and has an inclined surface 11 that forms an angle with an extension axis of the tube structure 20. The tube structure 20 is used for accommodating the optical fiber bundle 10, and binding the optical fiber bundle 10, so as to improve the aggregation performance of each optical fiber.

The output end of the optical fiber bundle 10 releases laser energy, and the inclined surface 11 is arranged at the output end, so that the optical fiber bundle 10 releases the laser energy towards one direction, namely towards a target area needing laser irradiation, the directivity of the released laser energy is stronger, the laser energy of the optical fiber bundle 10 is concentrated in the target area, the intensity of the laser energy irradiated to the target area is greatly increased, and the condition of insufficient laser irradiation energy is avoided. Wherein the arrows in fig. 1 indicate the release direction of the laser energy.

The laser ablation catheter 100 provided by the present embodiment is applicable to a variety of surgical scenarios including, but not limited to, ELCA and RDN.

As an embodiment, the output end of the fiber optic bundle 10 is located at the distal end of the tube structure 20, with an inclined surface 11 that is angled with respect to the axis of elongation of the tube structure 20; the method specifically comprises the following steps: the inclined surface 11 forms an included angle with the axis of the extending direction of the laser ablation catheter, which is larger than or equal to 20 degrees and smaller than or equal to 40 degrees. The included angle is set to be between 20 deg. and 40 deg. so that the laser energy is released from the optical fiber bundle 10 to the ablation site with a short travel.

Referring to fig. 3, the optical fiber bundle 10 includes a plurality of first optical fibers 12, wherein the core diameter of the first optical fibers 12 is smaller than the core diameter of the optical fiber bundle 10; the first optical fiber is used for delivering the first laser and releasing the first laser at the sympathetic nerve of the target site. In particular applications, the proximal end of the first optical fiber 12 receives the first laser light from the control system, releases the first laser light at the output end, and the released first laser light can irradiate the sympathetic nerve of the site to be ablated, thereby enabling the output end of the fiber bundle to irradiate the sympathetic nerve of the site to be ablated. Wherein the first laser may be continuous or transmitted in pulses.

As one embodiment, the bend radius of the first optical fiber 12 is less than 10mm and the core diameter of the first optical fiber 12 is less than 200um. The smaller the bending radius, the greater the flexibility of the optical fiber, so that the first optical fiber 12 has better flexibility, and the laser ablation catheter 100 can enter into a blood vessel with a large angle bend, thereby expanding the application range of the laser ablation catheter 100. For example, the laser ablation catheter 100 provided in this embodiment can be easily introduced into the renal arteries from the arterial trunk with a bend approaching 90 ° from the arterial trunk to the left and right renal arteries, and thus can be well applied to RDN surgery. In addition, the first optical fiber 12 provided in this embodiment not only makes the optical fiber bundle 10 easily pass through the blood vessel, but also reduces the power loss of the optical fiber bundle 10 and improves the light transmission efficiency of the optical fiber bundle 10. Preferably, the optical fiber bundle 10 includes at least seven first optical fibers 12, which effectively ensures the stability of the working performance of the optical fiber bundle 10. It will be appreciated that in other embodiments, it is possible that the optical fiber bundle 10 includes a first optical fiber 12 having a large bend radius.

As one embodiment, the core numerical aperture of the first optical fiber 12 is greater than or equal to 0.22 and less than or equal to 0.5. In particular applications, the first optical fiber 12 may be selected to have a corresponding core numerical aperture, depending on the circumstances.

Illustratively, the first optical fiber 12 is a silica optical fiber, and includes a core, a cladding that is wrapped around the core, and a coating layer that is coated on the outside of the cladding. Wherein the coating layer comprises polyimide and acrylic ester materials, so that the high temperature resistance of the coating layer is greatly improved; the cladding is a polymeric material that can be used at relatively low laser power and near infrared wavelengths.

Referring to fig. 2, 4 and 5, the optical fiber bundle 10 further includes a second optical fiber 13, and the second optical fiber 13 is used for sensing the temperature of the distal end of the optical fiber bundle 10 at the ablation site. In a specific application, the control system sends out the second laser to the second optical fiber 13, according to the effect of the second optical fiber 13, the control system receives the central reflection wavelength of the second optical fiber 13, and according to the central reflection wavelength, the temperature of the part to be ablated at the output end of the optical fiber bundle 10 can be judged, and the second optical fiber 13 plays a role of a temperature sensor. Therefore, when the first laser irradiation is carried out on the part to be ablated, the temperature of the part to be ablated can be monitored in real time, and the overhigh or overlow temperature is avoided, so that the stability and the safety of the first laser irradiation are improved. Of course, in other embodiments, the optical fiber bundle 10 may be provided without the second optical fiber 13.

As one embodiment, the second optical fiber 13 has a bending radius of greater than or equal to 10mm and less than or equal to 25mm; the core diameter of the second optical fiber 13 is greater than or equal to 8um and less than or equal to 12um. The arrangement is such that the second optical fiber 13 has a degree of flexibility to facilitate the passage of the bundle 10 through blood vessels of various degrees of curvature.

As an embodiment, the second optical fiber 13 is provided with one or more sets of fiber gratings. In this embodiment, the second optical fiber 13 is provided with a set of fiber gratings. In specific application, the number of the fiber gratings can be set according to actual requirements, and the number of the fiber gratings is not limited.

In this embodiment, the second optical fiber 13 is used as a temperature sensor to sense the temperature of the distal end of the optical fiber bundle 10 at the ablation site, and further, the second optical fiber 13 may be set as a resistance temperature device or a thermocouple or the like to perform a temperature sensing function, wherein the temperature measurement accuracy is +/-0.1 ℃.

As an embodiment, the optical fiber bundle 10 comprises a second optical fiber 13. It will be appreciated that in other embodiments, it is possible that the optical fibre bundle 10 comprises two or three or four second optical fibres 13. Here, the number of the second optical fibers 13 is not limited.

As an embodiment, the first optical fiber 12 is a multimode optical fiber, and the second optical fiber 13 is a single mode optical fiber or a multimode optical fiber. For example, in the present embodiment, the first optical fiber 12 is a multimode optical fiber, and the second optical fiber 13 is a single mode optical fiber.

Referring to fig. 2, 4 and 5, the tube structure 20 includes an outer tube 21 and an inner tube 22, the outer tube 21 is sleeved on the outer periphery of the inner tube 22 and eccentrically disposed with the inner tube 22 to form a first fiber placement channel 23, distal ends of the plurality of first optical fibers 12 are disposed in the first fiber placement channel 23, and a cavity of the inner tube 22 forms a second fiber placement channel 24 for passing a guide wire. The second optical fiber 13 may be located in the first optical fiber placement channel 23, and may share an input end of the optical fiber bundle and an output end of the optical fiber bundle with the first optical fiber 12, or may be located in the second optical fiber placement channel 24. In this way, accommodation of the first optical fiber 12 and the second optical fiber 13 is achieved. Preferably, the second optical fiber 13 is disposed in the second optical fiber disposition channel 24, and the installation is faster and more convenient than the installation of the first optical fiber 12 and the second optical fiber 13 in the same optical fiber disposition channel (because the radial dimensions of the first optical fiber 12 and the second optical fiber 13 are different, resulting in difficult installation and low concentration of the optical fibers).

In the present embodiment, the outer tube 21 and the inner tube 22 are disposed at the distal end of the laser ablation catheter 100, the distal end of the first optical fiber 12 is disposed in the first optical fiber placement channel 23, and the distal end of the second optical fiber 13 is disposed in the second optical fiber placement channel 24. Wherein the first optical fiber 12 and the second optical fiber 13 are fixed in the first optical fiber installation channel 23 and the second optical fiber installation channel 24, respectively, by an adhesive.

In this embodiment, the outer tube 21 and the inner tube 22 are eccentrically disposed, wherein the outer tube 21 and the inner tube 22 are both cylindrical, and both are eccentrically disposed, that is, the central axis of the outer tube 21 and the central axis of the inner tube 22 deviate from each other, the radial dimension of a partial region of the formed first optical fiber accommodating channel 23 is larger than the radial dimension of another partial region, and after the plurality of first optical fibers 12 are disposed in the first optical fiber accommodating channel 23, the first optical fibers 12 may be arranged in a crescent or crescent-like structure. Thus, the laser light released from the output end of the optical fiber 10 is more concentrated and directional, which is beneficial to increasing the intensity of the laser energy in the same direction. Preferably, the inner tube 22 is inscribed in the outer tube 21, and the cross section of the formed first optical fiber installation channel 23 is crescent-shaped, and the plurality of first optical fibers 12 are arranged in crescent shape after being placed in the first optical fiber installation channel 23.

In another embodiment, the inner tube 22 is replaced with an arcuate spacer. With this arrangement, the arcuate spacer separates the cavity of the outer tube 21 into a first cavity forming the first fiber placement channel 23 and a second cavity forming the second fiber placement channel 24. The isolating plate is arc-shaped, so that the cross section of the first cavity is crescent.

Referring to fig. 2, 4-6, the tube structure 20 further includes an outer sleeve 25, the outer sleeve 25 is disposed at the proximal end of the laser ablation catheter 100, and the first optical fiber 12 and the second optical fiber 13 are both accommodated in the outer sleeve 25. Specifically, the lumen of the outer cannula 25 forms a third fiber placement channel 26, the third fiber placement channel 26 communicating with the first fiber placement channel 23 and the second fiber placement channel 24, the proximal ends of the first optical fiber 12 and the second optical fiber 13 each being received in the third fiber placement channel 26.

As an embodiment, the outer tube 21 and the inner tube 22 are metal tubes, and the outer tube 25 is a quartz capillary tube having a thickness greater than that of the metal tubes. Illustratively, the outer sleeve 25 has an inner diameter of between 0.40mm and 0.80mm and an outer diameter of between 0.8mm and 1.2 mm.

The laser ablation catheter 100 further includes a balloon assembly sealingly sleeved over the distal end of the tube structure 20 along the extension of the catheter such that the inclined surface 11 is disposed within the balloon assembly.

Referring to fig. 2 and 4, the balloon assembly includes a first balloon 30, the first balloon 30 is hermetically sleeved on the distal end of the optical fiber bundle 10, and the inclined surface 11 is disposed in the first balloon 30. Specifically, the first balloon 30 is sealingly sleeved over the distal end of the tube structure 20. In this embodiment, the first balloon 30 is sealingly sleeved over the distal end of the outer tube 21.

The tube structure 20 is further provided with a first liquid guiding channel for delivering at least a first liquid to the first balloon 30. The first liquid may be a cooling liquid, such as cooling water. By feeding a cooling fluid into the first balloon 30, the distal end of the optical fiber bundle 10 can be cooled to avoid damage to the optical fiber bundle 10 caused by too high temperature during laser irradiation. In particular applications, after the cooling fluid is introduced into the first balloon 30 through the first fluid delivery channel, the cooling fluid absorbs heat from the distal end of the fiber optic bundle 10 and is then discharged from the first fluid delivery channel.

Referring to fig. 2 and 4, the laser ablation catheter 100 further includes a second balloon 40, and the second balloon 40 is sleeved on the periphery of the first balloon 30. Specifically, second balloon 40 is sealingly sleeved over the distal end of tube structure 20. In this embodiment, the second balloon 40 is sealingly sleeved on the distal end of the outer tube 21 and on the outer periphery of the first balloon 30.

The tube structure 20 is further provided with a second liquid guiding channel for delivering at least a second liquid for the second balloon 40. Wherein the second liquid may be a radio-opaque solution or physiological saline, etc. By inputting the second liquid into the second balloon 40 and pressurizing the second liquid inside the second balloon 40, the second balloon 40 is inflated, and the second balloon 40 can be tightly attached to the inner wall of the blood vessel, so that the laser ablation catheter 100 is positioned, and the stability of the laser ablation catheter 100 during laser irradiation is improved.

As an embodiment, both the first balloon 30 and the second balloon 40 may be connected to the tube structure 20 by hot melt welding or laser welding to ensure the reliability of the connection.

As an embodiment, the laser ablation catheter 100 further includes a rotating member, where the rotating member is connected to the proximal end of the tube structure 20, and is configured to drive the optical fiber bundle 10 and the tube structure 20 to rotate around the axial direction of the laser ablation catheter in a preset manner, so that the output laser of the optical fiber bundle can irradiate the ablation site at an angle of 360 °. Specifically, the rotating member is provided at the proximal end of the outer sleeve 25. Through setting up the rotating member, drive the rotating member rotation under the effect of external force to drive tube structure 20 and optic fibre bundle 10 all carry out 360 rotations around tube structure 20's axial, and then make the laser energy that optic fibre bundle 10 released throw with annular mode, can 360 global cover blood vessels, can shine the different directions in the blood vessel, improve the effect that laser irradiated greatly. Wherein, can rotate through manual drive rotating member, also can rotate through intelligent control drive rotating member.

Referring to fig. 1, 2 and 6, the rotating member is a luer adapter 70. Specifically, the luer adapter 70 is mounted to the proximal end of the outer sleeve 25, and the luer adapter 70 is manually driven to rotate the tube structure 20 and the optical fiber bundle 10.

Preferably, the preset mode is to emit laser light with a duration of 10 seconds or 15 seconds every 45 degrees or 90 degrees. I.e. laser light with a duration of 10 seconds is emitted every 45 degrees or 15 seconds is emitted every 90 degrees.

Referring to fig. 1 and 2, the laser ablation catheter 100 further includes a guidewire 50, the guidewire 50 being disposed through the tubular structure 20, the distal end of the tubular structure 20 being guided to the target site of the vessel by controlling the guidewire 50. Specifically, the guidewire 50 is disposed within the second fiber placement channel 24.

Referring to fig. 1, the laser ablation catheter 100 further includes a catheter hub 60, the catheter hub 60 being connected to the proximal end of the tube structure 20, the catheter hub 60 being provided with an infusion port for infusing a fluid into the balloon assembly.

Further, the embodiment of the present invention also provides a laser ablation system, which includes the laser ablation catheter 100. By employing the laser ablation catheter 100 described above, laser energy of sufficient intensity is released to fully meet the therapeutic needs.

As an embodiment, the laser ablation system further comprises a control system for controlling outputting laser light with a wavelength of 1064nm to the laser ablation catheter at least. Compared with the laser with other wavelengths, the laser with the wavelength of 1064nm has lower absorption in water, and photons can enter into the peripheral tissues of the renal artery blood vessels and cause strong scattering and thermal effects, so that effective injury of the renal artery adventitia is generated, and the irradiation effect on the sympathetic nerve fibers is better. The first laser light in the wavelength range is absorbed by the renal artery intima little, and the photothermal effect is low, so that the damage to the renal artery intima is small.

The foregoing description is only of the preferred embodiments of the present invention and is not intended to limit the scope of the invention, and all equivalent structural changes made by the description of the present invention and the accompanying drawings or direct/indirect application in other related technical fields are included in the scope of the invention.

Claims (12)

1. A laser ablation catheter, comprising:

An elongated tube structure comprising an inner tube and an outer tube; the outer layer pipe is sleeved on the periphery of the inner layer pipe, is eccentrically arranged with the inner layer pipe and surrounds the inner layer pipe to form a first optical fiber arranging channel, and the inner layer pipe is used for a guide wire to pass through;

an optical fiber bundle disposed within the tube structure; the output end of the optical fiber bundle is positioned at the far end of the pipe structure and is provided with an inclined surface which forms an angle with the extending axis of the pipe structure;

the optical fiber bundle comprises a plurality of first optical fibers, and the core diameter of the first optical fibers is smaller than that of the optical fiber bundle; the plurality of first optical fibers are arranged in the first optical fiber arrangement channel.

2. The laser ablation catheter of claim 1, further comprising a rotating member connected to the proximal end of the tube structure for driving the tube structure and the fiber bundle to rotate about the axis of the laser ablation catheter in a preset manner, such that the output laser of the fiber bundle irradiates the part to be ablated at an angle of 360 °.

3. The laser ablation catheter according to claim 2, wherein the rotating member is connected to the proximal end of the tube structure, and is configured to drive the tube structure and the optical fiber bundle to rotate around the axis of the laser ablation catheter in a preset manner, so that the output laser of the optical fiber bundle can irradiate the part to be ablated at an angle of 360 degrees, and the laser ablation catheter specifically includes:

The rotating member is a luer adapter,

The preset mode is to emit laser with the duration of 10 seconds or 15 seconds every 45 degrees or 90 degrees.

4. The laser ablation catheter of claim 1, further comprising a balloon assembly sealingly sleeved to the distal end of the tubular structure along the extension of the catheter such that the inclined surface is disposed within the balloon assembly.

5. The laser ablation catheter of claim 4, wherein the balloon assembly comprises a first balloon and/or a second balloon;

the first balloon and/or the second balloon are/is sleeved at the far end of the tube structure in a sealing way, the second balloon is sleeved at the periphery of the first balloon, the inclined surface is arranged in the first balloon, the first balloon is internally filled with first liquid for cooling the output end of the optical fiber bundle, and the second balloon is/is used for filling second liquid for positioning the tube structure at least.

6. The laser ablation catheter of claim 1, wherein the output end of the fiber optic bundle is located at the distal end of the tube structure, having an inclined surface that is angled with respect to the tube structure extension axis; the method specifically comprises the following steps: the inclined surface forms an included angle which is larger than or equal to 20 degrees and smaller than or equal to 40 degrees with the axis of the extending direction of the laser ablation catheter.

7. The laser ablation catheter of claim 1, wherein the fiber bundle further comprises a second optical fiber located within the first fiber placement channel, sharing the fiber bundle input end and the fiber bundle output end with the first optical fiber, or the second optical fiber is disposed within the inner tube; the second optical fiber is used for sensing the temperature of the distal end of the optical fiber bundle at the part to be ablated.

8. The laser ablation catheter of claim 1, wherein the first optical fiber has a bend radius of less than 10mm; and/or the core diameter of the first optical fiber is less than 200um.

9. The laser ablation catheter of claim 7, wherein the second optical fiber has a bend radius greater than or equal to 10mm and less than or equal to 25mm; and/or the core diameter of the second optical fiber is greater than or equal to 8um and less than or equal to 12um.

10. The laser ablation catheter of claim 4, further comprising: the catheter seat is connected with the proximal end of the tube structure, and is provided with a liquid injection port for injecting liquid into the balloon assembly.

11. A laser ablation system comprising a laser ablation catheter according to any one of claims 1 to 10.

12. The laser ablation system of claim 11, further comprising a control system for controlling outputting laser light at a wavelength of 1064nm to the laser ablation catheter.