Laser thermotherapy apparatus

Abstract

This application provides a laser hyperthermia device and a laser hyperthermia method. The laser hyperthermia device includes an ablation component and a laser probe. The ablation component emits laser light to ablate target tissue. The proximal end of the laser probe is connected to the optical path of the ablation component to conduct the laser light to the target tissue area. The laser probe includes a stator assembly and a rotor assembly arranged axially toward the distal end. The stator assembly is used to adjust at least one of the laser beam diameter, beam focal length, and light intensity. The rotor assembly is configured to rotate in a radial plane with the axial direction as the central axis to adjust the laser emission direction. The embodiments of this application enable more concentrated laser energy, thereby improving the accuracy of laser ablation, reducing energy requirements, and thus reducing ablation costs. During the rotation of the rotor assembly, the laser light is emitted toward the area of ​​the target tissue that needs ablation. Multiple ablations of the same target tissue can reduce the risk of infection of the ablation site and improve ablation efficiency.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and more specifically, to a laser thermotherapy device and a laser thermotherapy method. Background Technology

[0002] For small, scattered, or poorly located lesions in clinical practice, such as gliomas, epileptic foci, thyroid nodules, pulmonary nodules, spinal disc stenosis, or polyps, traditional open surgery is difficult to remove precisely and can easily damage normal tissue. This is especially true for lesions such as intraventricular gray matter heterotopia or hypothalamic hamartomas, where traditional open surgery carries a high risk of damaging normal tissue or leaving incomplete removal and potential complications.

[0003] Laser thermotherapy has shown good therapeutic effects and promising application prospects for the aforementioned conditions. Currently available laser thermotherapy technologies generally use lasers ranging from 980 nanometers to 1064 nanometers, which are delivered via laser probes to the target tissue (such as the lesion area requiring thermotherapy) to achieve ablation.

[0004] However, the laser probes used in these technologies emit lasers with low precision and poor flexibility, making it difficult to accurately ablate irregular target tissue areas. Utility Model Content

[0005] This application addresses the shortcomings of existing methods by proposing a laser thermotherapy device and method to solve the technical problem of low accuracy of laser emitted from the laser probe in related technologies.

[0006] In a first aspect, embodiments of this application provide a laser thermotherapy device, comprising:

[0007] Ablation components are used to emit lasers to ablate target tissue;

[0008] The laser probe, with its proximal end connected to the optical path of the ablation component, is used to conduct laser light to the target tissue area. The laser probe includes a stator assembly and a rotor assembly arranged sequentially toward the distal end along the axial direction. The stator assembly is used to adjust at least one of the laser beam diameter, beam focal length, and light intensity. The rotor assembly is configured to rotate in a radial plane with the axial direction as the central axis, and is used to adjust the laser light output direction.

[0009] In some possible embodiments, it also includes:

[0010] The imaging component is used to emit a laser to image the target tissue area and is connected to the near-end optical path of the laser probe.

[0011] In some possible embodiments, it also includes:

[0012] The switching device is connected to the optical paths of both the ablation component and the imaging component at its proximal end, and to the optical path of the laser probe at its distal end. It is used to control the type of laser entering the laser probe. The laser types include lasers used for ablation and lasers used for imaging.

[0013] In some possible embodiments, the stator assembly includes: a collimation assembly, a beam expander assembly, and a zoom assembly arranged sequentially toward the distal end along the axial direction;

[0014] The beam diameter of the laser output by the beam expander is matched with the aperture of the zoom component.

[0015] In some possible embodiments, the beam expander assembly includes at least two beam expander lenses with different focal lengths arranged sequentially toward the distal end along the axial direction, wherein the focal length of the beam expander lens closer to the proximal end of the laser probe is shorter than the focal length of the beam expander lens farther from the proximal end of the laser probe.

[0016] In some possible embodiments, the zoom assembly includes at least one of a distorting mirror, a spatial light modulator, or a zoom lens;

[0017] In some possible embodiments, the zoom assembly includes at least two zoom lenses arranged sequentially toward the distal end along the axial direction; the focal length of the zoom lenses is not less than 5 mm and not more than 20 mm;

[0018] In some possible embodiments, the zoom range of the zoom assembly's output end is not less than 1 mm and not more than 20 mm.

[0019] In some possible embodiments, the rotor assembly includes: a hollow rotary motor, a variable refractive index lens sandwiched in the hollow portion of the rotary motor, and a reflector fixed relative to the variable refractive index lens;

[0020] The optical axis of a variable refractive index lens forms an angle with the reflecting surface of a mirror.

[0021] In some possible embodiments, the reflector is a right-angle prism, comprising two transmission surfaces perpendicular to each other and a reflection surface at an acute angle to the transmission surfaces.

[0022] In some possible embodiments, the transmission surface is bonded to the light-emitting surface of the variable refractive index lens.

[0023] In some possible embodiments, the rotor assembly further includes: a sleeve, which is closed at the distal end and fitted around the variable refractive index lens and the reflector, with a transparent window on the sidewall near the distal end;

[0024] The two transmission surfaces are respectively attached and connected to the inner sidewall of the sleeve and the inner endwall of the distal end;

[0025] The reflective surface faces the window.

[0026] Secondly, embodiments of this application also provide a laser thermotherapy method, employing any of the laser thermotherapy devices described in the first aspect above, comprising:

[0027] Obtain lesion information from the target tissue to determine the corresponding laser ablation mode;

[0028] The laser probe is controlled according to the laser ablation mode to adjust at least one of the following: beam diameter, beam focal length, light intensity, light output direction, and light output position.

[0029] The beneficial technical effects of the technical solutions provided in this application include:

[0030] In this embodiment, the laser is emitted from the ablation assembly to the laser probe. The stator assembly of the laser probe alters at least one of the laser beam diameter and intensity, making the laser energy more concentrated. This improves the accuracy of laser ablation, reduces energy requirements, and consequently lowers ablation costs. The laser emitted from the stator assembly is conducted to the target tissue via the rotor assembly. As the rotor assembly rotates in the radial plane, the laser is directed towards the area of ​​the target tissue requiring ablation. Multiple ablations of the same target tissue can be performed without repeatedly changing the laser probe, enabling precise ablation of irregular target tissues. This reduces the risk of infection during ablation and improves ablation efficiency.

[0031] Additional aspects and advantages of this application will be set forth in part in the description which follows, and will become apparent from the description or may be learned by practice of this application. Attached Figure Description

[0032] The above and / or additional aspects and advantages of this application will become apparent and readily understood from the following description of the embodiments taken in conjunction with the accompanying drawings, wherein:

[0033] Figure 1 This is a schematic diagram of the structure of a laser thermotherapy device provided in an embodiment of this application;

[0034] Figure 2 for Figure 1 A magnified view of a combination of a variable refractive index lens and a mirror at point A in the middle;

[0035] Figure 3 for Figure 1 A magnified view of another type of variable refractive index lens and mirror combination at point A;

[0036] Figure 4 This is a schematic flowchart of a laser thermotherapy method provided in an embodiment of this application.

[0037] Figure label:

[0038] 100-Laser thermotherapy equipment;

[0039] 10-Ablation component;

[0040] 20 - Laser probe;

[0041] 21-Stator assembly;

[0042] 211-Collimation Component;

[0043] 2111 - Gradient index lens;

[0044] 212-Beam expander assembly;

[0045] 2121 - Short focal length lens; 2122 - Long focal length lens;

[0046] 213 - Zoom assembly;

[0047] 2131 - First zoom lens; 2132 - Second zoom lens;

[0048] 22-Rotor assembly;

[0049] 221 - Rotary motor; 222 - Variable refractive index lens;

[0050] 223 - Mirror;

[0051] 2231 - Transmitting surface; 2232 - Reflecting surface;

[0052] 224-Sleeve;

[0053] 2241 - Window; 2242 - Transparent Window;

[0054] 30 - Imaging component; 40 - Switching device; 50 - Translation component. Detailed Implementation

[0055] The embodiments of this application are described below with reference to the accompanying drawings. It should be understood that the embodiments described below with reference to the accompanying drawings are exemplary descriptions for explaining the technical solutions of the embodiments of this application, and do not constitute a limitation on the technical solutions of the embodiments of this application.

[0056] Those skilled in the art will understand that, unless specifically stated otherwise, the terms "described" and "the" as used herein may also include plural forms. It should be further understood that the term "comprising" as used in the specification of this application means the presence of the stated features, integers, elements, and / or components, but does not exclude implementations of other features, information, data, operations, elements, components, and / or combinations thereof supported by the art. The term "and / or" as used herein refers to at least one of the items defined by the term; for example, "A and / or B" can be implemented as "A," or as "B," or as "A and B."

[0057] To make the objectives, technical solutions, and advantages of this application clearer, the embodiments of this application will be described in further detail below with reference to the accompanying drawings.

[0058] First, let's introduce and explain several terms used in this application:

[0059] Laser interstitial thermotherapy (LITT) is a treatment method that uses the thermal effect of lasers to destroy target tissue. The basic principle is based on stereotactic techniques from neurosurgery, where an optical fiber is placed into the brain. During treatment, approximately 10-15W of infrared laser light is transmitted through the fiber to the probe. The probe scatters the laser light, thereby heating the brain tissue surrounding the probe and achieving ablation. Currently, there are two commonly used LITT systems internationally, using lasers with wavelengths of 1064 nm and 980 nm respectively, with a brain tissue penetration range of 2-10 nanometers.

[0060] Currently, laser probes are mainly divided into two categories: the first type scatters the laser, emitting a relatively uniform laser beam in all directions for overall ablation, and is usually a relatively regular cylindrical shape; the second type reflects the laser from the side of the probe, ablates a portion of the target tissue in a directional manner, and then completes the overall ablation of the surrounding target tissue by rotating the angle several times, which has better controllability and improved accuracy.

[0061] However, the laser precision emitted by the laser probes used in related technologies is still not high enough, and the flexibility is poor, making it difficult to accurately ablate irregular target tissue areas.

[0062] The laser thermotherapy equipment and laser thermotherapy method provided in this application are intended to solve the above-mentioned technical problems in related technologies.

[0063] The technical solution of this application and how it solves the above-mentioned technical problems are described in detail below with specific embodiments. It should be noted that the following embodiments can be referenced, borrowed, or combined with each other, and the same terms, similar features, and similar implementation steps in different embodiments will not be described again.

[0064] This application provides a laser hyperthermia device 100, the structural schematic diagram of which is shown below. Figure 1 As shown, it includes: ablation component 10 and laser probe 20.

[0065] The ablation component 10 is used to emit a laser to ablate the target tissue.

[0066] The proximal end of the laser probe 20 is optically connected to the ablation assembly 10 to conduct laser light to the target tissue area. The laser probe 20 includes a stator assembly 21 and a rotor assembly 22 arranged sequentially toward the distal end along the axial direction. The stator assembly 21 is used to adjust at least one of the laser beam diameter, beam focal length, and light intensity. The rotor assembly 22 is configured to rotate in a radial plane with the axial direction as the central axis to adjust the laser light output direction.

[0067] In this embodiment, the laser is emitted from the ablation component 10 to the laser probe 20. The stator component 21 of the laser probe 20 alters at least one of the laser beam diameter, beam focal length, and intensity, thereby concentrating the laser energy, improving the accuracy of laser ablation, reducing energy requirements, and ultimately lowering ablation costs. The laser emitted from the stator component 21 is conducted to the target tissue via the rotor component 22. During the rotation of the rotor component 22, the laser is directed towards the area of ​​the target tissue that needs ablation. Multiple ablations of the same target tissue can be performed without repeatedly replacing the laser probe 20, enabling precise ablation of irregular target tissues. This reduces the risk of infection during ablation and improves ablation efficiency.

[0068] Optionally, the ablation component 10 can be a high-power infrared laser with a wavelength range of 920 nm to 1100 nm (inclusive), exhibiting good penetration into target tissue, and a power range of 2 watts to 10 watts (inclusive). The ablation component 10 has a built-in laser power adjustment device that can rapidly modulate the light intensity with a response time of less than 1 microsecond. Furthermore, the high-power infrared laser's output port is fused with an optical fiber with a ferrule at one end for laser transmission; the ferrule diameter is between 1.25 mm and 2.5 mm (inclusive).

[0069] Optionally, the stator assembly 21 and the rotor assembly 22 are coaxially arranged, that is, the optical axes of the stator assembly 21 and the rotor assembly 22 are collinear.

[0070] Optionally, such as Figure 1 As shown, the laser thermotherapy device 100 also includes a translation component 50, such as a precision displacement stage.

[0071] The translation component 50 is axially movable to the laser probe 20, which drives the laser probe 20 to move along the axis, thereby adjusting the laser emission position along the axis.

[0072] It is understandable that the axial direction refers to the axial direction of the laser probe 20.

[0073] It should be noted that the proximal end refers to the end closer to the operator, while the distal end refers to the end farther from the operator and closer to the target tissue.

[0074] In some possible embodiments, such as Figure 1As shown, the laser thermotherapy device 100 also includes an imaging component 30.

[0075] The imaging component 30 is used to emit a laser to image the target tissue area and is connected to the near-end optical path of the laser probe 20.

[0076] In this embodiment, the imaging component 30 can emit a laser to image the target tissue area, such as a probe laser. The laser is transmitted to the target tissue through the laser probe 20. Under the action of the stator component 21, at least one of the laser beam diameter or light intensity is adjusted to obtain the desired laser. The rotor component 22 and the translation component 50 perform a spiral scan to obtain at least one of the size, shape and position of the target tissue, thereby obtaining more accurate size or contour information of the target tissue. This facilitates the development of a targeted laser ablation plan and the determination of the laser nature emitted by the ablation component 10.

[0077] Optionally, the imaging component 30 may include an OCT (Optical Coherence Tomography) imaging module, which uses a low-power probe laser with a wavelength range of 1310±100 nanometers (including upper and lower limits).

[0078] In some possible embodiments, such as Figure 1 As shown, the laser thermotherapy device 100 also includes a switching device 40.

[0079] The near end of the switching device 40 is optically connected to both the ablation assembly 10 and the imaging assembly 30, and the far end is optically connected to the near end of the laser probe 20, which is used to control the type of laser entering the laser probe 20; the laser type includes lasers for ablation and lasers for imaging.

[0080] In this embodiment, the ablation component 10 and the imaging component 30 share a single laser probe 20. The switching device 40 is located between the ablation component 10 and the laser probe 20, and also between the imaging component 30 and the laser probe 20. It can control the optical path switching state between the ablation component 10 and the laser probe 20, and also between the imaging component 30 and the laser probe 20, thereby controlling the type of laser entering the laser probe 20. The laser type can be switched as needed, eliminating the need to configure separate probes for the ablation component 10 and the imaging component 30. This avoids problems such as a high risk of wound infection, complex operation, or low efficiency caused by repeated probe insertion and removal.

[0081] Optionally, the OTC imaging module and the high-power infrared laser are connected to the switching device 40 via an optical fiber coupling interface, and are connected to and share a laser probe 20 through the switching device 40.

[0082] In some possible embodiments, such as Figure 1As shown, the stator assembly 21 includes a collimation assembly 211, a beam expander assembly 212, and a zoom assembly 213 arranged sequentially along the axial direction toward the far end.

[0083] The beam diameter of the laser output by the beam expander 212 is matched with the aperture of the zoom component 213.

[0084] In this embodiment, the collimation component 211, beam expander 212, and zoom component 213 collimate, expand, and zoom the laser used for ablation and imaging, respectively, to obtain a more concentrated laser energy. The aperture refers to the diameter of the circular hole generated at the center of the zoom component 213 by the variable aperture. The beam diameter of the laser output from the beam expander 212 matches the aperture, allowing the laser output from the beam expander 212 to essentially fill the aperture, thereby increasing the numerical aperture and helping to reduce the injected single-pulse energy, thus reducing cell damage. Furthermore, the optical power per unit area is lower than the damage threshold of the zoom component 213, ensuring that the laser power is controlled within a safe range and protecting the zoom component 213 from damage.

[0085] Optionally, the collimation component 211 includes a graded-index lens 2111.

[0086] In some possible embodiments, the beam expander assembly 212 includes at least two beam expander lenses with different focal lengths arranged sequentially toward the distal end along the axial direction, wherein the focal length of the beam expander lens closer to the proximal end of the laser probe 20 is shorter than the focal length of the beam expander lens farther from the proximal end of the laser probe 20.

[0087] In this embodiment, as Figure 1 As shown, the beam-expanding lens near the laser probe 20 can be called the short focal length lens 2121, and the beam-expanding lens farther from the laser probe 20 can be called the long focal length lens 2122. The combination of the short focal length lens 2121 and the long focal length lens 2122 can achieve beam expansion of approximately 5 times, so that the laser beam emitted from the beam-expanding assembly 212 fills the light-transmitting aperture of the zoom assembly 213, increasing the numerical aperture entering the rotor of the laser probe 20. The optical power per unit area is lower than the damage threshold of the zoom device to protect the device.

[0088] Optionally, the beam expander 212 may include at least one of a graded refractive index lens, a spherical lens group, and an aspherical lens, with a beam expansion magnification of 2 to 7 times, so that the laser beam emitted from the beam expander 212 fills the light-transmitting aperture of the zoom component 213 and increases the numerical aperture entering the rotor of the laser probe 20.

[0089] In some possible embodiments, zoom assembly 213 includes at least one of a morphing mirror, a spatial light modulator, and a zoom lens.

[0090] In some possible embodiments, the zoom assembly 213 includes at least two zoom lenses arranged sequentially toward the distal end along the axial direction; the focal length of the zoom lenses is not less than 5 mm and not more than 20 mm.

[0091] In this embodiment, two zoom lenses are used as an example. Along the axial direction, they are a first zoom lens 2131 and a second zoom lens 2132, both with focal lengths between 5 mm and 20 mm (including the endpoint value). They can change the divergence angle of the laser entering the rotor, thereby controlling the zoom range of the end of the laser probe 20 between 1 mm and 20 mm.

[0092] In some possible embodiments, the zoom range of the output end of the zoom assembly 213 is not less than 1 mm and not more than 20 mm. The zoom assembly 213 can pre-compensate for the aberrations of the laser probe 20, so that the laser focusing accuracy is higher than 50 micrometers. The zoom assembly 213 is used to zoom the laser transmitted within the laser probe 20 to perform targeted resection of tissues at different radial depths, thereby achieving precise ablation of lesions with arbitrary radial contours.

[0093] This embodiment utilizes the laser focusing and zoom design of the laser probe 20, along with aberration compensation, to concentrate laser energy, thereby significantly improving the precision of laser ablation to the 50-micron level, or the precision of a single cell. Simultaneously, laser focusing reduces the energy requirement for ablation, avoiding problems such as tissue carbonization or probe tip damage caused by excessively high local temperatures. Furthermore, the ablation contour can be customized for irregular lesions. For example, firstly, a 3D scan is performed using the laser emitted by the imaging component 30 to observe the size and location of the target tissue, obtaining more accurate information about its size or contour. Then, an intelligent algorithm plans the point scanning trajectory for laser ablation, actively avoiding normal tissue areas (such as blood vessels and important brain regions), ensuring that only the target tissue is ablated, thus possessing high safety.

[0094] In some possible embodiments, such as Figures 1-3 As shown, the rotor assembly 22 includes: a hollow rotary motor 221, a variable refractive index lens 222 sandwiched in the hollow part of the rotary motor 221, and a reflector 223 fixedly disposed relative to the variable refractive index lens 222.

[0095] The optical axis of the variable refractive index lens 222 forms an angle with the reflecting surface 2232 of the mirror 223.

[0096] In this embodiment, the rotary motor 221 has a hollow structure design and is used to clamp the variable refractive index lens 222 and the reflector 223 at the end.

[0097] Optionally, the rotational accuracy of the rotary motor 221 is higher than 1 milliradian (mrad) and the displacement accuracy is better than 10 micrometers, which can ensure the accuracy of damage to the target tissue.

[0098] Optionally, the diameters of both the variable refractive index lens 222 and the end reflector 223 are between 1 mm and 3 mm. The variable refractive index lens 222 can be a graded refractive index lens, which can exceed one pitch, effectively increasing the optical path. The numerical aperture of this graded refractive index lens is 0.1 mm to 0.5 mm (including the endpoint value), and the overall length ranges from 50 mm to 150 mm (including the endpoint value), allowing for selection of different lengths depending on the depth of implantation into the target tissue.

[0099] Optionally, the reflector 223 is a total reflection mirror 223 or a coated reflector 223, with a laser reflectivity of more than 95% for 920 nm to 1350 nm (including the endpoint value), which can improve the utilization rate of light.

[0100] In some possible embodiments, the reflector 223 is a right-angle prism, including two transmission surfaces 2231 at right angles to each other, and a reflection surface 2232 at an acute angle to the transmission surfaces 2231.

[0101] In this embodiment, light enters the right-angle prism from one transmission surface 2231, is reflected on the reflection surface 2232, and finally exits from another transmission surface 2231, changing the direction of light propagation.

[0102] Optionally, the light-emitting surface of the reflector 223 includes an aberration-optimized optical element, which mainly refers to a spherical or aspherical mirror, and can be fixed to the light-emitting surface of the reflector 223 by bonding or 3D printing technology.

[0103] It is understood that the light-emitting surface of the reflector 223 can be either the transmission surface 2231 or the reflection surface 2232 of the reflector 223. For details, please refer to the following embodiments.

[0104] In some possible embodiments, such as Figure 2 As shown, the transmission surface 2231 is bonded to the light-emitting surface of the variable refractive index lens.

[0105] In this embodiment, the variable refractive index lens 222 and the reflector 223 can be directly combined by means of optical adhesive, etc., and the laser propagation direction can be changed by 90° through total internal reflection, so that the laser is output radially with the axial direction as the central axis, so as to remove tissues at different radial depths.

[0106] In some possible embodiments, such as Figure 3 As shown, the rotor assembly 22 also includes: a sleeve 224, which is closed at the distal end and is fitted around the variable refractive index lens and the reflector 223, and has a transparent window 2241 on the side wall near the distal end.

[0107] The two transmission surfaces 2231 are respectively attached to the inner wall of the sleeve 224 and the inner wall of the distal end.

[0108] The reflective surface 2232 faces the window 2241.

[0109] In this embodiment, the rotor assembly 22 is composed of a rotary motor 221, a variable refractive index lens 222, a reflector 223 at the end, and a sleeve 224. The variable refractive index lens 222 and the reflector 223 at the end are coupled and fixed through the sleeve 224. The sleeve 224 can be made of metal or other rigid light-shielding materials, providing good light-shielding and stability. A window 2241 is required on the side wall near the far end for light transmission, and a transparent window 2242 is installed at the window 2241 to enclose it, preventing tissue from entering the laser probe 20 through the window 2241 and affecting the laser ablation effect.

[0110] Optionally, the transparent window 2242 can be an aberration-optimizing optical element to compensate for the aberrations of the variable refractive index lens 222 and improve the focusing accuracy of the laser emitted from the laser probe 20. The transparent window 2242 can be a spherical mirror or an aspherical mirror, and can also be fixed to the light-emitting surface of the reflector 223 by bonding or 3D printing technology.

[0111] Optionally, the laser thermotherapy device includes a control host and a computer program stored on the control host. The control host executes the computer program to implement the steps of the laser thermotherapy method provided in this application.

[0112] Based on the same inventive concept, this application also provides a laser hyperthermia method, using any of the laser hyperthermia devices 100 provided in the above embodiments. A flowchart of this method is shown below. Figure 4 As shown, steps S101 to S102 are included:

[0113] S101: Obtain lesion information of the target tissue and determine the corresponding laser ablation mode.

[0114] S102: Control the laser probe 20 to adjust at least one of the following according to the laser ablation mode: beam diameter, beam focal length, light intensity, light output direction, and light output position.

[0115] In this embodiment, the control host in the laser thermotherapy device 100 can control the ablation component 10 to emit laser for ablation, control the stator component 21 of the laser probe 20 to adjust at least one of the laser beam diameter, beam focal length and light intensity, control the rotor component 22 of the laser probe 20 to adjust the light output direction, and can also control the laser probe 20 to translate along the axial direction to adjust the light output position.

[0116] The laser thermotherapy method provided in this application will be described in detail below using specific implementation steps as an example.

[0117] First, the optical path connection between the imaging component 30 and the laser probe 20 can be switched via the switching device 40. The imaging component 30 performs preoperative OCT imaging on the target tissue, conducting 3D scanning to observe lesion information such as the size, location, or outline of the lesions. Furthermore, the control host can analyze the OCT imaging data to extract more accurate lesion information.

[0118] Secondly, based on the lesion information, the control host controls the ablation component 10 to emit the corresponding laser, controls the stator component 21 to adjust the laser, controls the rotor component 22 to change the light output direction, and controls the translation component 50 to move the laser probe 20 to perform spiral scanning for precise ablation.

[0119] After the first ablation, the switching device 40 connects to the imaging component 30 to perform a 3D spiral scan to observe the ablation effect on the target tissue and evaluate the lesion damage. If the preset thermotherapy effect is achieved, the ablation ends. If the preset thermotherapy effect is not achieved, the switching device 40 is controlled to switch the imaging component 30 again to reacquire lesion information and continue ablation.

[0120] By applying the embodiments of this application, at least the following beneficial effects can be achieved:

[0121] 1. The laser is emitted from the ablation component 10 to the laser probe 20. The stator component 21 of the laser probe 20 changes at least one of the laser beam diameter, beam focal length and light intensity, which can make the laser energy more concentrated, thereby improving the accuracy of laser ablation, reducing energy demand, and thus reducing ablation cost.

[0122] 2. The laser emitted from the stator assembly 21 is transmitted to the target tissue through the rotor assembly 22. During the rotation of the rotor assembly 22, the laser is directed towards the area in the target tissue that needs to be ablated. Multiple ablations can be performed on the same target tissue without having to replace the laser probe 20 multiple times. This can achieve precise ablation of irregular target tissue, reduce the risk of infection of the wound during ablation, and improve ablation efficiency.

[0123] 3. The rotor assembly 22 and the translation assembly perform a spiral scan to obtain at least one of the size, shape and position of the target tissue, so as to obtain more accurate size or contour information of the target tissue, which is convenient for developing a targeted laser ablation plan and determining the laser nature emitted by the ablation assembly 10.

[0124] 4. The laser output from the beam expander 212 can essentially fill the light-transmitting aperture, thereby increasing the numerical aperture and helping to reduce the injected single-pulse energy, thus reducing cell damage. Moreover, the optical power per unit area is lower than the damage threshold of the zoom component 213, ensuring that the laser power is controlled within a safe range and protecting the zoom component 213 from damage.

[0125] 5. The variable refractive index lens 222 and the reflector 223 can be directly combined by means of optical adhesive, etc., and the laser propagation direction can be changed by 90° through total internal reflection, so that the laser is output radially with the axial direction as the central axis, so as to remove tissues at different radial depths.

[0126] 6. The sleeve 224 can be made of metal or other rigid light-shielding materials, possessing good light-shielding properties and stability. A window 2241 needs to be opened on the side wall near the far end for light transmission, and a transparent window 2242 is installed at the window 2241 to enclose it, preventing tissue from entering the laser probe 20 through the window 2241 and affecting the laser ablation effect. The transparent window 2242 can be an aberration-optimizing optical element used to compensate for the aberrations of the variable refractive index lens 222.

[0127] Those skilled in the art will understand that the steps, measures, and solutions in the various operations, methods, and processes discussed in this application can be alternated, modified, combined, or deleted. Furthermore, other steps, measures, and solutions in the various operations, methods, and processes discussed in this application can also be alternated, modified, rearranged, decomposed, combined, or deleted. Furthermore, steps, measures, and solutions in related technologies that are similar to those disclosed in this application can also be alternated, modified, rearranged, decomposed, combined, or deleted.

[0128] In the description of this application, the terms "center," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," and "outer," etc., indicate directions or positional relationships based on the exemplary directions or positional relationships shown in the accompanying drawings. They are used to facilitate the description or simplification of the embodiments of this application and are not intended to indicate or imply that the device or component referred to must have a specific orientation or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this application.

[0129] The terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Therefore, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this application, unless otherwise stated, "a plurality of" means two or more.

[0130] In the description of this application, it should be noted that, unless otherwise expressly specified and limited, the terms "installation," "connection," and "joining" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a direct connection or an indirect connection through an intermediate medium; and they can refer to the internal communication between two components. Those skilled in the art can understand the specific meaning of the above terms in this application based on the specific circumstances.

[0131] In the description of this specification, specific features, structures, materials, or characteristics may be combined in any suitable manner in one or more embodiments or examples.

[0132] The above description is only a partial implementation of this application. It should be noted that for those skilled in the art, other similar implementation methods based on the technical concept of this application, without departing from the technical concept of this application, also fall within the protection scope of the embodiments of this application.

Claims

1. A laser thermotherapy device, characterized in that, include: Ablation components are used to emit lasers to ablate target tissue; A laser probe, with its proximal end connected to the optical path of an ablation component, is used to conduct laser light to the target tissue area. The laser probe includes a stator assembly and a rotor assembly arranged sequentially toward the distal end along the axial direction. The stator assembly is used to adjust at least one of the laser beam diameter, beam focal length, and light intensity. The rotor assembly is configured to rotate in a radial plane with the axial direction as the central axis, and is used to adjust the laser light output direction.

2. The laser thermotherapy device according to claim 1, characterized in that, Also includes: An imaging component for emitting a laser to image a target tissue region is connected to the near-end optical path of the laser probe.

3. The laser thermotherapy device according to claim 2, characterized in that, Also includes: The switching device is connected to the optical paths of both the ablation component and the imaging component at its proximal end, and to the optical path of the laser probe at its distal end, for controlling the type of laser entering the laser probe; the laser type includes lasers for ablation and lasers for imaging.

4. The laser thermotherapy device according to claim 1, characterized in that, The stator assembly includes: a collimation assembly, a beam expander assembly, and a zoom assembly arranged sequentially toward the distal end along the axial direction; The beam diameter of the laser output by the beam expander is matched with the aperture of the zoom component.

5. The laser thermotherapy device according to claim 4, characterized in that, The beam expander assembly includes at least two beam expander lenses with different focal lengths arranged sequentially toward the distal end along the axial direction, wherein the focal length of the beam expander lens closer to the proximal end of the laser probe is shorter than the focal length of the beam expander lens farther from the proximal end of the laser probe.

6. The laser thermotherapy device according to claim 4, characterized in that, Includes at least one of the following: The zoom assembly includes at least one of a distorting mirror, a spatial light modulator, and a zoom lens; The zoom assembly includes at least two zoom lenses arranged sequentially toward the distal end along the axial direction; the focal length of the zoom lenses is not less than 5 mm and not more than 20 mm; The zoom range of the output end of the zoom component is not less than 1 mm and not more than 20 mm.

7. The laser thermotherapy device according to claim 1, characterized in that, The rotor assembly includes: a hollow rotary motor, a variable refractive index lens sandwiched in the hollow part of the rotary motor, and a reflector fixedly disposed relative to the variable refractive index lens; The optical axis of the variable refractive index lens forms an angle with the reflecting surface of the mirror.

8. The laser thermotherapy device according to claim 7, characterized in that, The reflector is a right-angle prism, comprising two transmission surfaces at right angles to each other, and a reflection surface at an acute angle to the transmission surfaces.

9. The laser thermotherapy device according to claim 8, characterized in that, The transmission surface is fitted and connected to the light-emitting surface of the variable refractive index lens.

10. The laser thermotherapy device according to claim 8, characterized in that, The rotor assembly further includes: a sleeve, which is closed at the distal end and is fitted around the variable refractive index lens and the reflector, with a transparent window on the side wall near the distal end; The two transmission surfaces are respectively attached and connected to the inner sidewall and the distal inner endwall of the sleeve; The reflective surface faces the window.

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