WO2023051672A1 - 一种用于消融手术光纤的护套结构 - Google Patents

一种用于消融手术光纤的护套结构 Download PDF

Info

Publication number
WO2023051672A1
WO2023051672A1 PCT/CN2022/122499 CN2022122499W WO2023051672A1 WO 2023051672 A1 WO2023051672 A1 WO 2023051672A1 CN 2022122499 W CN2022122499 W CN 2022122499W WO 2023051672 A1 WO2023051672 A1 WO 2023051672A1
Authority
WO
WIPO (PCT)
Prior art keywords
sheath
optical fiber
ablation
reflective film
optical path
Prior art date
Application number
PCT/CN2022/122499
Other languages
English (en)
French (fr)
Inventor
金慧杰
夏良道
Original Assignee
杭州佳量医疗科技有限公司
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 杭州佳量医疗科技有限公司 filed Critical 杭州佳量医疗科技有限公司
Publication of WO2023051672A1 publication Critical patent/WO2023051672A1/zh

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
    • A61B2018/2238—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor with means for selectively laterally deflecting the tip of the fibre

Definitions

  • the invention relates to the technical field of medical instruments, in particular to a sheath structure for ablation operation optical fibers.
  • optical fiber is usually used as the transmission medium of laser, and the range and direction of the light output of the optical path are determined by the type of optical fiber.
  • laser ablation there are three fiber types commonly used: dispersion fiber, ring fiber and side-firing fiber. These three fiber types have different light output ranges.
  • the light output mode of the ring fiber is output along the entire circumference of the radial direction;
  • the light output mode of the front end of the diffuse fiber is output along the radial direction and along the axial direction according to a predefined length. ;
  • the front-end light output mode of the side-firing fiber will be output along the radial side.
  • the embodiment of the present invention aims to provide a sheath structure for an optical fiber in ablation surgery, so as to solve the problem that the existing optical fiber cannot perform precise conformal ablation of tumors.
  • the invention provides a sheath structure for optical fiber in ablation operation, which includes a sheath and an optical path adjustment component;
  • the optical path of the laser can perform conformal ablation on the target lesion area.
  • the optical path adjustment component is a reflective film, and the reflective film is arranged on the side wall of the sheath.
  • the reflective film is provided on the inner wall and/or the outer wall of the sheath.
  • the range of emitted light from the sheath can be changed .
  • the sheath is an elongated tubular structure.
  • cross-sectional shape of the sheath is a regular or irregular ring.
  • the optical path adjustment component further includes an anti-reflection film, and the anti-reflection film is arranged on the opposite side of the reflective film.
  • the optical path adjustment component is a lens structure, and the lens structure is located on the side wall of the sheath.
  • the optical path adjustment assembly further includes a lens structure, and the reflective film and the lens structure are respectively located on both sides of the optical fiber.
  • the lens structure is a converging mirror or a diverging mirror.
  • the present invention can achieve at least one of the following beneficial effects:
  • the present invention is equipped with an optical path adjustment component on the sheath.
  • the path of the laser light emitted by the optical fiber can be changed through the optical path adjustment component arranged on the sheath, so that the laser can complete the target lesion area
  • the tumor can be ablated without considering the influence of tumor location, shape and size, avoiding technical difficulties, cost increase and inconvenient operation caused by avoiding obstacles on the channel.
  • the sheath structure of various shapes of the present invention realizes the side emission light of the dispersed optical fiber; by making a corresponding reflective layer or optical lens structure on the sheath, the side emission light of the dispersed optical fiber is realized, and can be according to actual needs Secondary adjustment of light divergence angle and ablation range.
  • Fig. 1 is the sheath structure schematic diagram of specific embodiment
  • Fig. 2 is the sheath structure cross-sectional schematic diagram (1) of specific embodiment 1;
  • Fig. 3 is the sheath structure cross-sectional schematic diagram (two) of specific embodiment 1;
  • Fig. 4 is the sheath structure cross-sectional schematic diagram (three) of specific embodiment 1;
  • Fig. 5 is the sheath structure cross-sectional schematic view (four) of specific embodiment 1;
  • Fig. 6 is the sheath structure cross-sectional schematic diagram (five) of specific embodiment 1;
  • Fig. 7 is the sheath structure cross-sectional schematic diagram (6) of specific embodiment 1;
  • Fig. 8 is a schematic cross-sectional view (seven) of the sheath structure of the specific embodiment 1;
  • Fig. 9 is a schematic cross-sectional view (eight) of the sheath structure of the specific embodiment 1;
  • Fig. 10 is a schematic diagram of the sheath structure of specific embodiment 2;
  • Fig. 11 is the sheath structure schematic diagram (1) of specific embodiment 3;
  • Fig. 12 is the sheath structure schematic diagram (two) of specific embodiment 3;
  • Fig. 13 is a schematic cross-sectional view (1) of the sheath structure of specific embodiment 4.
  • Fig. 14 is a schematic cross-sectional view (two) of the sheath structure of specific embodiment 4.
  • Fig. 15 is a schematic cross-sectional view (three) of the sheath structure of the specific embodiment 4;
  • Fig. 16 is a schematic cross-sectional view (four) of the sheath structure of specific embodiment 4.
  • Fig. 17 is a schematic cross-sectional view (five) of the sheath structure of specific embodiment 4.
  • Fig. 18 is a schematic cross-sectional view (6) of the sheath structure of the specific embodiment 4;
  • Fig. 19 is a cross-sectional schematic diagram (7) of the sheath structure of specific embodiment 4.
  • Fig. 20 is a schematic cross-sectional view (eight) of the sheath structure of Embodiment 4.
  • connection should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection , can be mechanically connected, can also be electrically connected, can be directly connected, and can also be indirectly connected through an intermediary.
  • connection should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection , can be mechanically connected, can also be electrically connected, can be directly connected, and can also be indirectly connected through an intermediary.
  • top, bottom, above, bottom and “on” are used throughout the description to refer to relative positions of components of the device, such as top and bottom substrates inside the device relative position. It will be appreciated that the devices are multifunctional independent of their orientation in space.
  • the laser can be irradiated to the lesion in a precise and conformal manner, the creator made multi-directional adjustments to the invasive surgical instrument for ablation on the basis of the existing technology and defects.
  • the ablation fiber taking the ablation fiber as an example to illustrate: 1.
  • the control and control of the light output direction only depend on the wavelength of the laser source itself and the type of fiber. That is to say, on the basis of selecting a certain fiber type, the optical path to the lesion is uniquely determined.
  • the optical fiber can only be moved or rotated axially to change the direction of light transmission, but whether it is axial Both movement and rotation will reduce the coupling efficiency of the fiber, thereby affecting the ablation result.
  • an optical path adjustment component is configured on the fiber sheath (not the fiber itself), which realizes multiple adjustments to the laser light path, and avoids the mechanical action of directly moving or rotating the fiber in the axial direction, ensuring good light output.
  • precise conformal ablation of the lesion can be achieved, which further improves the utilization rate of light energy for ablation.
  • sheath structure for ablation operation optical fiber, as shown in Fig. 1-Fig.
  • the sheath 101 is an elongated tubular structure, and the optical fiber 200 is located in the lumen of the sheath 101 .
  • the optical path adjustment component is configured on the sheath 101 integrally and/or separately. The optical path adjustment component can change the laser optical path emitted by the optical fiber 200 in the sheath 101 so as to perform precise conformal ablation on the target lesion area 300 .
  • an optical path adjustment component is provided on the sheath, and when the optical fiber is used for ablation surgery, the optical path adjustment component arranged on the sheath changes or By changing the laser transmission path emitted by the optical fiber twice, the conformal ablation of the tumor in the target lesion area can be completed without considering the position, shape and size of the tumor, which makes the preoperative planning of laser ablation surgery easier and faster.
  • the irregularity of the ablation range caused by the change of the optical path transmission by the optical path adjustment component can flexibly avoid damage to important tissues near the operation channel.
  • the sheath 101 has a certain hardness, and its material is preferably PC (Polycarbonate; polycarbonate) plastic.
  • the sheath 101 has the function of protecting the optical fiber 200 and isolating the direct contact between the optical fiber 200 and the tissue. , to prevent the optical fiber 200 from damaging human tissue.
  • the cancerous cells in the target lesion area 300 are ablated by using the optical fiber 200 arranged in it. 200 establishes the effect of the ablation channel.
  • the optical path adjustment component is disposed on the side wall of the sheath 101 .
  • the optical path adjustment assembly is arranged close to the front end of the sheath 101, that is, the optical path adjustment assembly corresponds to the position of the light output portion of the optical fiber 200. set up.
  • the laser transmission path emitted by the optical fiber 200 can be adjusted as required, and the adjusted laser path can be more targeted to the target lesion area 300.
  • Conformal ablation compared with the manufacturing process of optical fibers, it is easier to design and manufacture the sheath structure, so various forms of sheath structures for ablation optical fibers can be manufactured, providing surgical operators with a wider range of choices Sex, making laser ablation surgery easier.
  • the present invention will be described in detail by taking a brain tumor as an example and integrating laser ablation technology.
  • sheath structure for ablation operation optical fiber
  • the sheath structure includes a sheath 101 and an optical path adjustment assembly
  • the optical path adjustment component is arranged at the front end of the side wall of the sheath 101 , and the optical path adjustment component can change the optical path of the laser light emitted by the optical fiber 200 in the sheath 101 to ablate the target lesion area 300 .
  • FIG. 2-FIG. 9, FIG. 11-FIG. 12, FIG. 14, FIG. 16, FIG. 18 and FIG. 20 the ablation range covered by the emitted light of the sheath structure is the ablation area 301.
  • the optical path adjustment component is a reflective film 102
  • the reflective film 102 is arranged on the side wall of the sheath 101, and the reflective film 102 can convert the incident light becomes parallel light and emits it.
  • the reflective film 102 is pasted on the wall of the sheath 101 .
  • the reflective film 102 has both a coverage length along the axial direction of the sheath 101 and a coverage width along the circumferential direction of the sheath 101.
  • the coverage mentioned below refers to the reflective film 102 along the Circumferential coverage of the sheath 101 .
  • the reflective film 102 can be arranged on the inner wall of the sheath 101. Considering that the reflective film 102 will reflect and lose part of the energy with the inner wall when it is on the outer wall, the Described reflective film 102 is arranged on inner wall and can avoid the energy loss of laser, guarantees the efficiency of laser; As shown in Figure 5, described reflective film 102 also can be located at sheath 101 outer wall, described reflective film 102 is located on outer wall It is more convenient to operate.
  • the reflective film 102 is provided on the inner wall of the sheath 101 .
  • the luminescent film 102 is arranged on the inner wall or the outer wall to have the same effect on adjusting the light path.
  • the reflective film 102 can also be provided on the inner wall of the sheath 101 or on the outer wall of the sheath 101 , and details will not be repeated in other embodiments.
  • the reflective film 102 can also be provided on the inner wall and the outer wall of the sheath 101 at the same time. Under this structure, since the reflective film 102 on the inner and outer walls of the overlapping area does not work, the reflective film on the inner wall 102 and the reflective film 102 arranged on the outer wall are selected according to requirements.
  • the optical fiber 200 Since the optical fiber 200 is set in the sheath 101, when the fiber head of the optical fiber 200 emits laser light, the laser light is irradiated on the reflective film 102, and then emitted as parallel light, so that the laser light emitted by the optical fiber 200 can be directed towards the reflective light.
  • the opposite direction of the film 102 is gathered to ablate the target lesion area 300 in this direction.
  • the uniformity of light output is further enhanced, and the light energy irradiated on the target lesion area 300 is more uniform;
  • the light paths are all emitted towards the same direction, which increases the damage force of the light energy, and the ablation range of the target lesion area 300 is expanded under the condition that the laser power remains unchanged.
  • the optical fiber 200 can be a ring optical fiber or a diffuse optical fiber, that is to say, when the optical fiber 200 emits light in the circumferential direction, the reflective film 102 is arranged at any position on the front end of the inner wall of the sheath 101, and the optical fiber 200 emits The laser light emitted by the optical fiber 200 is directly emitted from the part where the reflective film 102 is not installed, and the laser light emitted by the optical fiber 200 is reflected back at the position where the reflective film 102 is installed, and merged with the directly emitted laser light to the target lesion area 300 .
  • the inner wall of the sheath 101 is a curved surface
  • the area covered by the reflective film 102 on the inner wall of the sheath 101 and the shape of the curved surface will affect the route of reflected light. That is to say, the coverage area of the reflective film 102 on the sheath 101 can be changed and/or the shape of the inner wall of the sheath 101 can be changed to obtain different light output ranges, so as to meet the different ranges and directions of the target lesion area 300. ablation.
  • sheath 101 By changing the inner wall structure of the sheath 101 with the reflective film 102 and the position of the optical fiber 200 relative to the reflective film 102 to obtain different light emission ranges, important tissues such as blood vessels and hippocampus can be avoided. Only three types of sheath structures are listed below.
  • the cross section of the sheath 101 is an irregular ring (the inner and outer walls of the sheath 101 are both irregular circles), including an upper half ring and a lower half ring, the upper half ring is The reflective film 102 is not provided on the semicircular ring, and the reflective film 102 is provided on the inner wall of the lower semicircular ring.
  • the arc surface of the inner wall of the lower semicircle is more gentle than the arc surface of the inner wall of the upper semicircle, and the reflective film 102 is set on the gentle inner wall, and the central angle of the part of the sheath 101 that does not cover the reflective film 102 (The included angle between the boundary of the light emitting range of the sheath 101 and the center of the optical fiber 200) is not greater than 90°, so that the laser light emitted by the optical fiber 200 finally converges into a small range of emitting angles, such as a right angle or an acute angle.
  • a reflective film 102 is provided on the gentle inner wall of the sheath 101. From the cross-section of the sheath structure, the central angle of the part of the sheath 101 not covered with the reflective film 102 is not greater than 90°.
  • the laser light emitted by the optical fiber 200 is emitted in a small angle range to ablate the target lesion region 300 , and the range covered by the emitted light is the ablation region 301 .
  • the cross section of the sheath 101 is an irregular ring (the inner wall of the sheath 101 is an irregular circle, and the outer wall is a regular circle), and the reflective film is arranged on the inner wall of the sheath 101 102, the central angle of the part of the sheath 101 not covered by the reflective film 102 is not greater than 90°, and the reflective film 102 covers most of the inner wall of the sheath 101, so that the laser light emitted by the optical fiber 200 is finally converged into a small range of output Angles, such as acute angles, ablate the target lesion area 300 .
  • the cross section of the sheath 101 is a regular ring (the inner and outer walls of the sheath 101 are regular circles), the reflective film 102 is set on the inner wall of the sheath 101, and the sheath
  • the central angle of the part of the sleeve 101 that does not cover the reflective film 102 is not greater than 90°, so that the laser light emitted by the optical fiber 200 is finally converged into a small range of outgoing angles, such as a right angle or an acute angle.
  • the cross section of the sheath 101 is a regular ring (the inner and outer walls of the sheath 101 are regular circles), the reflective film 102 is set on the outer wall of the sheath 101, and the sheath
  • the central angle of the part of the sleeve 101 that does not cover the reflective film 102 is not greater than 90°, so that the laser light emitted by the optical fiber 200 is finally converged into a small range of outgoing angles, such as a right angle or an acute angle. It is understandable that the same effect can be achieved by disposing the reflective film 102 on the outer wall of the sheath 101 with other cross-sectional structures (as shown in FIGS. 2-4 ), and details will not be repeated here.
  • the central angle of the portion not covered by the reflective film 102 can also be changed within 90° ⁇ 180°.
  • Form 2 As shown in Figure 6, the outer wall of the sheath 101 is a regular circle, the inner wall is an irregular circle, the inner wall includes an upper arc surface and a lower arc surface, the upper arc surface is concentric with the outer wall, and the lower arc surface
  • the outer wall is concentric, the lower arc surface is provided with the reflective film 102, and the wall thickness of the inner wall side with the reflective film 102 is greater than the wall thickness of the inner wall without the reflective film 102, so that the curvature of the lower arc surface is greater than that of the upper arc surface , this structure makes the lower arc surface close to the axis of the optical fiber 200, and the reflective film 102 is arranged on the lower arc surface.
  • the part of the sheath 101 that does not cover the reflective film 102 The central angle is 180°, so that the laser light emitted by the optical fiber 200 is finally converged into a range of 180° to be emitted, and the target lesion area 300 can be ablated in a range of 180°.
  • the inner wall and the outer part of the sheath 101 are regular circles, and the reflective film 102 is provided on the inner wall surface. From the cross section of the sheath structure, the sheath 101 is not covered with the reflective film The central angle of the part 102 is 180°, so that the laser light emitted by the optical fiber 200 is finally converged into a range of 180° to emit, and the target lesion area 300 can be covered and ablated in a range of 180°.
  • the outer wall of the sheath 101 is a regular circle, the inner wall is an irregular circle, the inner wall includes an upper arc surface and a lower arc surface, the upper arc surface is concentric with the outer wall, and the lower arc surface is not aligned with
  • the outer wall is concentric, the lower arc surface is provided with the reflective film 102, and the wall thickness of the inner wall side with the reflective film 102 is greater than the wall thickness of the inner wall without the reflective film 102, so that the curvature of the lower arc surface is greater than that of the upper arc surface , this structure makes the lower arc surface close to the axis of the optical fiber 200, and the reflective film 102 is arranged on the lower arc surface.
  • the part of the sheath 101 that does not cover the reflective film 102 The central angle is greater than 180°, so that the laser emitted by the optical fiber 200 is finally converged into a range with an angle greater than 180°, so that a wider coverage and ablation of the target lesion area 300 can be performed.
  • the outer wall and inner wall of the sheath 101 are regular circles, and the reflective film 102 is provided on the inner wall surface. From the cross-section of the sheath structure, the sheath 101 is not covered with reflective film. The central angle of the part of the membrane 102 is greater than 180°, so that the laser light emitted by the optical fiber 200 is finally converged to a range greater than 180°, and the target lesion area 300 can be ablated in a wider range.
  • the cross-section of the sheath 101 can be a regular ring or an irregular ring, by changing the coverage of the reflective film 102 and/or relative to the optical fiber The position of 200 can get different light emitting ranges.
  • the cross section of the sheath 101 is a regular ring, and the inner wall is provided in the form of a reflective film 102 .
  • FIG. 10 discloses a sheath structure (hereinafter referred to as "sheath structure") for ablation surgical optical fibers.
  • the difference from Embodiment 1 is that the The optical path adjustment component includes a reflective film 102 and an anti-reflective film 103.
  • the anti-reflective film 103 is arranged on the opposite side of the reflective film 102, thereby increasing the light transmission of the sheath 101, reducing or eliminating stray light, so that the laser emitted by the optical fiber 200 As much as possible is irradiated to the target lesion area 300 for ablation.
  • the target lesion area 300 can obtain more laser light to achieve a better ablation effect.
  • Other structures and beneficial effects are the same as those in Embodiment 1, and will not be repeated here.
  • sheath structure for ablation surgical optical fibers
  • the sheath structure includes a sheath 101 and an optical path An adjustment assembly
  • the optical path adjustment assembly is arranged at the front end of the side wall of the sheath 101, and the optical path adjustment assembly can change the optical path of the laser light emitted by the optical fiber 200 in the sheath 101 to ablate the target lesion area 300 .
  • the optical path adjustment component is a lens structure 104, and the lens structure 104 can change the size and/or shape of the ablation range. Because of the increase of the lens structure 104, the original circular ablation area is transformed into an ablation area 301 in the shape shown in Fig. 11 and Fig. 12, and more irregular tumors can be adapted.
  • the lens structure 104 is located on the sheath 101. Understandably, the lens structure 104 can be provided on the inner wall of the sheath 101 as a separate component, for example, the lens structure 104 can be pasted on the inner wall of the sheath 101, or can be used as a A part of the sheath 101 .
  • the lens structure 104 and the sheath 101 are an integral structure.
  • the lens structure 104 can also be fabricated on the side wall of the sheath 101 , and the lens structure 104 is embedded in a groove provided on the side wall of the sheath 101 .
  • the lens structure 104 may be a converging lens or a diverging mirror, wherein the concentrating mirror is preferably a convex lens, and the diverging mirror is preferably a concave lens.
  • the lens structure 104 is a convex lens, and the laser light emitted by the optical fiber 200 diverges in the circumferential direction, and becomes parallel light after passing through the convex lens, which can locally highlight and/or deepen the target lesion at the location of the lens structure 104 Ablation of region 300 .
  • the lens structure 104 is a concave lens, and the laser light emitted by the optical fiber 200 diverges in the circumferential direction, and becomes more divergent after passing through the concave lens, which expands the coverage of the light emitted by the lens structure 104 and enhances the ablation effect.
  • a lens structure 104 is provided on the sheath 101.
  • the lens structure 104 is specifically arranged at the front end of the side wall of the sheath 101.
  • the optical fiber 200 is used for ablation surgery, it is arranged on the The lens structure 104 on the sheath 101 changes the path of the laser light emitted by the optical fiber 200, so the ablation of tumors with irregular shapes becomes more flexible and easy to operate.
  • sheath structure for ablation surgical optical fibers
  • the sheath structure includes a sheath 101 and an optical path An adjustment assembly
  • the optical path adjustment assembly is arranged at the front end of the side wall of the sheath 101, and the optical path adjustment assembly can change the optical path of the laser light emitted by the optical fiber 200 in the sheath 101 to ablate the target lesion area 300 .
  • the optical path adjustment component includes a reflective film 102 and a lens structure 104, the reflective film 102 is used to direct the light emitted by the optical fiber 200 to the direction of the target lesion area 300, so as to realize unidirectional emission; the reflective film 102 Cooperating with the lens structure 104 can adapt to more tumors of different shapes.
  • the reflective film 102 and the lens structure 104 are disposed opposite to each other, and are respectively located on two sides of the optical fiber 200 .
  • the lens structure 104 is a convex lens, and the laser light emitted in the circumferential direction of the optical fiber 200 is returned to the convex lens in parallel when it encounters the reflective film 102 and then focused.
  • the optical fiber 200 directly passes through the convex lens to form The parallel light beam can enhance the ablation of a certain area of the target lesion area 300 .
  • the lens structure 104 is a concave lens, and the laser light emitted in the circumferential direction of the optical fiber 200 is returned to the concave lens in parallel after encountering the reflective film 102, and is refracted by the concave lens and emitted at a larger refraction angle. , together with the optical fiber 200 directly passing through the light beam refracted by the concave lens, can enhance the ablation of a specific range of the target lesion area 300 .
  • the coverage area of the reflective film 102 and the structure of the arc-shaped surface where the reflective film 102 is provided can also be changed to obtain different light output ranges, as shown in Embodiment 1 above, and will not be repeated here. repeat.
  • an optical path adjustment component is arranged on the sheath to change the light output trajectory of the optical fiber.
  • the various shapes of the sheath structure of the present invention realize the dispersion of the light emitted from the side of the optical fiber; through the corresponding reflective layer or optical lens structure on the sheath, the side emission of the dispersed optical fiber is realized, and the light can be adjusted according to actual needs Divergence angle and ablation range.

Landscapes

  • Health & Medical Sciences (AREA)
  • Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Medical Informatics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Electromagnetism (AREA)
  • Optics & Photonics (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Otolaryngology (AREA)
  • Molecular Biology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Radiation-Therapy Devices (AREA)
  • Laser Surgery Devices (AREA)

Abstract

本发明涉及一种用于消融手术光纤的护套结构，属于医疗器械技术领域，解决了现有技术中光纤无法对肿瘤进行精准适形消融的问题。本发明包括护套和光路调节组件；所述光路调节组件设于所述护套上，且能够改变位于所述护套内的光纤发出的激光的光路以对目标病灶区域进行适形消融。本发明能够对目标病灶区域进行精准适形消融。

Description

一种用于消融手术光纤的护套结构
相关申请的交叉引用
本申请要求于2021年09月30日申请的，申请号为202111165503.0，名称为“一种用于消融手术光纤的护套结构”的中国专利申请的优先权。
技术领域
本发明涉及医疗器械技术领域，尤其涉及一种用于消融手术光纤的护套结构。
背景技术
近年来，磁共振成像引导的激光间质热疗在治疗肿瘤方面显示出广泛的临床应用价值。该技术是利用激光释放的热量对病变组织进行消融，被认为是一种比开放手术侵入性更小的手术。但该项消融手术仍有其突出的缺点：难以做到精准适形消融。临床已知的肿瘤的形状有多种多样，有息肉状、乳头状、结节状、分叶状、囊状、弥漫性肥厚状、溃疡状、浸润性包块状等等。想要对各种形态的肿瘤进行精准适形消融，一是需要精准无误的手术规划，例如，针对某一特定的肿瘤形状给出一个或多个手术通道，然后一次性使用一种或多种不同型号的光纤进行消融；二则是要依靠于对激光能量的灵活调控。
现阶段通常采用光纤作为激光的传输介质，光路的出光范围及方向均由光纤型号来决定。在激光消融术中，常用的有弥散光纤、环形光纤和侧射光纤三种光纤型号。这三种光纤型号均有不同的出光范围，例如，环形光纤的前端出光方式为沿径向全周输出；弥散光纤的前端出光方式为沿径向并且沿轴向按预先定义的长度全周输出；侧射光纤的前端出光方式将为沿径向侧面输出。
因此，想要做到精准的适形消融，就要尽可能的使操作者在激光消融手术时根据术前规划和肿瘤形状灵活调整出光方向和/或出光范围。然而，目前激光消融手术在国内还未广泛推行，市面上也鲜有在既定的光纤型号下，可再次灵活调控出光方向和/或出光范围的消融光纤护套或类似产品。
发明内容
鉴于上述的分析，本发明实施例旨在提供一种用于消融手术光纤的护套结构，用以解决现有光纤无法对肿瘤进行精准适形消融的问题。
本发明提供了一种用于消融手术光纤的护套结构，包括护套和光路调节组件；所述光路调节组件设于所述护套上，且能够改变位于所述护套内的光纤发出的激光的光路以对目标病灶区域进行适形消融。
进一步地，所述光路调节组件为反光膜，所述反光膜设于所述护套的侧壁上。
进一步地，所述反光膜设于所述护套的内侧壁上和/或外侧壁上。
进一步地，通过改变所述反光膜沿所述护套的侧壁周向的覆盖范围和/或改变所述反光膜所在所述护套的侧壁的形状能够改变所述护套的出射光范围。
进一步地，所述护套为细长的管状结构。
进一步地，所述护套的横截面形状为规则或非规则的圆环。
进一步地，所述光路调节组件还包括增透膜，所述增透膜设于所述反光膜的相对侧。
进一步地，所述光路调节组件为透镜结构，所述透镜结构位于所述护套的侧壁面上。
进一步地，所述光路调节组件还包括透镜结构，所述反光膜和所述透镜结构分别位于所述光纤的两侧。
进一步地，所述透镜结构为聚光镜或发散镜。
与现有技术相比，本发明至少可实现如下有益效果之一：
(1)本发明在护套上设有光路调节组件，当光纤用于消融手术时，通过设置于护套上的光路调节组件改变光纤发出的激光的路径，即可使激光完成对目标病灶区域的肿瘤进行消融，不用考虑肿瘤位置、形状和大小的影响，避免了为了避开通道上的阻碍而带来的技术困难、成本增加及操作不便等问题。
(2)本发明的多种形状的护套结构，实现了弥散光纤侧射出光；通过护套上做相应的反射层或者光学透镜结构，实现了弥散光纤的侧射出光，并可以按实际需求二次调整光的发散角及消融范围。
本发明中，上述各技术方案之间还可以相互组合，以实现更多的优选组合方案。本发明的其他特征和优点将在随后的说明书中阐述，并且，部分优点可从说明书中变得显而易见，或者通过实施本发明而了解。本发明的目的和其他优点可通过说明书以及附图中所特别指出的内容中来实现和获得。
附图说明
附图仅用于示出具体实施例的目的，而并不认为是对本发明的限制，在整个附图中，相同的参考符号表示相同的部件。
图1为具体实施例的护套结构示意图；
图2为具体实施例1的护套结构横截面示意图(一)；
图3为具体实施例1的护套结构横截面示意图(二)；
图4为具体实施例1的护套结构横截面示意图(三)；
图5为具体实施例1的护套结构横截面示意图(四)；
图6为具体实施例1的护套结构横截面示意图(五)；
图7为具体实施例1的护套结构横截面示意图(六)；
图8为具体实施例1的护套结构横截面示意图(七)；
图9为具体实施例1的护套结构横截面示意图(八)；
图10为具体实施例2的护套结构示意图；
图11为具体实施例3的护套结构示意图(一)；
图12为具体实施例3的护套结构示意图(二)；
图13为具体实施例4的护套结构横截面示意图(一)；
图14为具体实施例4的护套结构横截面示意图(二)；
图15为具体实施例4的护套结构横截面示意图(三)；
图16为具体实施例4的护套结构横截面示意图(四)；
图17为具体实施例4的护套结构横截面示意图(五)；
图18为具体实施例4的护套结构横截面示意图(六)；
图19为具体实施例4的护套结构横截面示意图(七)；
图20为具体实施例4的护套结构横截面示意图(八)。
附图标记：
101-护套；102-反光膜；103-增透膜；104-透镜结构；
200-光纤；300-目标病灶区域；301-消融区域。
具体实施方式
下面结合附图来具体描述本发明的优选实施例，其中，附图构成本发明一部分，并与本发明的实施例一起用于阐释本发明的原理，并非用于限定本发明的范围。
在本发明实施例的描述中，需要说明的是，除非另有明确的规定和限定，术语“相连”应做广义理解，例如，可以是固定连接，也可以是可拆卸连接，或一体地连接，可以是机 械连接，也可以是电连接，可以是直接相连，也可以通过中间媒介间接相连。对于本领域的普通技术人员而言，可以根据具体情况理解上述术语在本发明中的具体含义。
全文中描述使用的术语“顶部”、“底部”、“在……上方”、“下”和“在……上”是相对于装置的部件的相对位置，例如装置内部的顶部和底部衬底的相对位置。可以理解的是装置是多功能的，与它们在空间中的方位无关。
基于改善消融光纤出光方向和出光范围灵活可控、精准适形地将激光照射至病灶的目的，创作者在现有技术和缺陷的基础上，对消融用侵入式手术器械进行了多方位的调整，以消融光纤为例进行说明：1、不用对消融用光纤本身作进一步优化设计，避免了光纤制作的工艺难题，降低开发成本；2、现有光纤及护套结构较为固定，对病灶消融范围的控制和出光方向的控制仅仅依赖于激光源本身的波长大小和光纤型号。也就是说，在选定了某一光纤型号的基础上，照射至病灶上的光路也就唯一确定，手术期间只能对光纤进行轴向移动或旋转改变光的传输方向，但无论是轴向移动还是旋转都将会使光纤的耦合效率变低，进而影响消融结果。而本申请在光纤护套上(非光纤本身)配置光路调节组件，实现了对激光光路的多次调节，并避免了直接对光纤进行轴向移动或旋转的机械动作，在保证了良好出光的前提下，又能做到对病灶的精准适形消融，进一步提高了消融用光能的利用率。
至此，本发明提出了一种用于消融手术光纤的护套结构(以下简称“护套结构”)，如图1-图20所示，所述护套结构包含一护套101，所述护套101为一细长的管状结构，光纤200位于所述护套101的管腔内。光路调节组件被一体式和/或分体式的配置于所述护套101上。所述光路调节组件能够改变位于所述护套101内的光纤200发出的激光光路以便对目标病灶区域300进行精准适形消融。
与现有技术相比，本实施例提供的护套结构，在所述护套上设有光路调节组件，当光纤用于消融手术时，通过设置于所述护套上的光路调节组件改变或二次改变光纤发出的激光传输路径，在不考虑肿瘤位置、形状和大小的情况下即可完成对目标病灶区域内肿瘤的适形消融，进而使激光消融手术的术前规划变得简单快捷。同时，借助于光路调节组件对光路传输的改变所带来的消融范围的不规则性可以灵活避开对手术通道附近的上重要组织的伤害。
在优选的实施例中，所述护套101具备有一定的硬度，其材质优选PC(Polycarbonate；聚碳酸酯)塑料，所述护套101有保护光纤200的作用，隔绝光纤200与组织直接接触，避免所述光纤200损伤人体组织。考虑到所述护套101需要伸到人体组织内，利用其内设置的光纤200对目标病灶区域300的癌变细胞进行消融，所述护套101的前端设有一定的锥度，可以起到为光纤200建立消融通道的作用。所述光路调节组件设于所述护套101的侧壁上。由于所述光纤200的出光位置为所述光纤200的前端，因而，所述光路调节组件靠近所述护套101的前端设置，即所述光路调节组件相应于所述光纤200的出光部位置而设置。
通过在护套101的侧壁上设置能够多次改变光路的光路调节组件，将光纤200发出的激光传输路径根据需要进行调节，调节后的激光路径可以更有针对性地对目标病灶区域300进行适形消融。此外，相较于光纤的制造工艺而言，对护套的结构设计和制作更为容易，因此可以制造出多种形式的消融光纤的护套结构，为手术操作者提供了更为广泛的选择性，让激光消融手术变得更为简单。以下将以脑肿瘤为例，集合激光消融技术对本发明做出详细的阐述。
实施例1
本发明的一个具体实施例，如图1图9所示，公开了一种用于消融手术光纤的护套结构(以下简称“护套结构”)，护套结构包括护套101和光路调节组件，所述光路调节组件设于所述护套101的侧壁前端，所述光路调节组件能够改变位于所述护套101内的光纤 200发出的激光的光路以对目标病灶区域300进行消融。图2-图9、图11-图12、图14、图16、图18及图20中，所述护套结构的出射光能够覆盖的消融范围为消融区域301。
请再次参阅图1，在本实施例1中，所述光路调节组件为反光膜102，所述反光膜102设于所述护套101的侧壁上，所述反光膜102能够将入射的光变为平行光并射出。具体地，所述反光膜102粘贴在所述护套101的壁上。
需要说明的是，所述反光膜102在护套101上既有沿护套101轴向的覆盖长度，也有沿护套101周向的覆盖宽度，以下所提到的覆盖均指反光膜102沿护套101周向的覆盖范围。
如图1-图4、图6-图9所示，所述反光膜102可以设在护套101的内壁，考虑到所述反光膜102在外壁时会与内壁发生反射损耗一部分能量，将所述反光膜102设在内壁上可以避免激光的能量损耗，保证激光的效率；如图5所示，所述反光膜102也可以设在护套101外壁，将所述反光膜102设在外壁上更加方便操作。优选的，将所述反光膜102设于护套101的内壁上。所述发光膜102设在内壁或外壁上对于光路的调节作用相同。
需要说明的，在其他实施例中，反光膜102同样既可以设在护套101的内壁，也可以设在护套101的外壁，在其他实施例中，不再一一赘述。
值得注意的是，反光膜102也可以同时设于护套101的内壁和外壁上，此种结构下，由于位于重叠区内外壁上的反光膜102不起作用，因而设在内壁上的反光膜102和设在外壁上的反光膜102根据需求进行方案选择。
由于所述光纤200设于所述护套101内，当光纤200的光纤头发出激光时，激光照射到反光膜102上，然后被以平行光射出，使得所述光纤200发出的激光可以朝向反光膜102的相对的方向聚集，用于消融该方向上的目标病灶区域300。一方面，由于平行光的射出，进一步增强了出光的均匀性，照射在所述目标病灶区域300的光能就越均匀；另一方面，反光膜102二次改变了光路传输路线，使所有的光路都朝向同一方向射出，增大了光能的损毁力度，在激光功率不变的情况下，对所述目标病灶区域300的消融范围扩大。
优选的，所述光纤200可为环形光纤或者弥散光纤，也就是说所述光纤200为周向出光时，所述反光膜102设置于护套101的内壁前端的任意位置，所述光纤200发出的激光在没有设置反光膜102的部分直接射出，在设置反光膜102的位置将所述光纤200发出的激光反射回去，与直接射出的激光汇合至目标病灶区域300。
本实施例1中，通过在所述护套101的内壁上设置发光膜102，将光纤200射出的光线全部导向目标病灶区域300的方向，以实现激光沿光纤20单侧方向的发射，可以针对特定部位的目标病灶区域300进行消融。此时，弥散光纤配合护套也能实现侧射出光。
可理解地，由于所述护套101内壁为弧形面，所述反光膜102在护套101内壁上覆盖的面积以及弧形面的形状将影响反射光的线路。也就是说可以改变所述反光膜102在护套101上的覆盖面积和/或改变护套101内壁形状来获得不同的出光范围，以满足对所述目标病灶区域300的不同范围、不同方向的消融。
通过改变所述护套101设有反光膜102侧的内壁结构及光纤200相对于反光膜102的位置来获取不同的出光范围，可以避让开重要的组织比如血管、海马体等。以下仅列出3种形式的护套结构。
形式一：如图2所示，所述护套101的横截面为非规则圆环(护套101的内、外壁均为非规则圆形)，包括上半圆环和下半圆环，上半圆环未设置所述反光膜102，下半圆环的内壁设有所述反光膜102，下半圆环的曲率大于上半圆环的曲率，且下半圆环靠近所述光纤200的轴心，下半圆环的内壁弧面比上半圆环的内壁弧面更加平缓，在平缓的内壁上设置所述反光膜102，所述护套101未覆盖反光膜102的部分的圆心角(护套101的出光范围边界与光纤200的中心的夹角)不大于90°，使得所述光纤200发出的激光最后汇聚成小范围出射角度，比如直角或者成锐角。
本实施例中，在所述护套101的平缓内壁上设有反光膜102，从护套结构的横截面看，所述护套101未覆盖反光膜102的部分的圆心角不大于90°，使得光纤200发出的激光以较小的角度范围出射，对目标病灶区域300进行消融，出射光能够覆盖的范围为消融区域301。
如图3所示，所述护套101的横截面为非规则圆环(护套101的内壁为非规则圆形，外壁为规则圆形)，在护套101的内壁上设置所述反光膜102，所述护套101未覆盖反光膜102的部分的圆心角不大于90°，且反光膜102覆盖护套101的绝大部分内壁，使得所述光纤200发出的激光最后汇聚成小范围出射角度，比如锐角，对目标病灶区域300进行消融。
如图4所示，所述护套101的横截面为规则圆环(护套101的内、外壁均为规则圆形)，在护套101的内壁上设置所述反光膜102，所述护套101未覆盖反光膜102的部分的圆心角不大于90°，使得所述光纤200发出的激光最后汇聚成小范围出射角度范围，比如直角或者成锐角。
如图5所示，所述护套101的横截面为规则圆环(护套101的内、外壁均为规则圆形)，在护套101的外壁上设置所述反光膜102，所述护套101未覆盖反光膜102的部分的圆心角不大于90°，使得所述光纤200发出的激光最后汇聚成小范围出射角度范围，比如直角或者成锐角。可理解的，在其他横截面结构的护套101(如图2-图4)的外壁上设置反光膜102能够达到相同的效果，在此不再一一赘述。
可理解的，通过改变所述反光膜102在护套101上的覆盖范围也可得到未覆盖反光膜102部分的圆心角在90°～180°内变动。
形式二：如图6所示，所述护套101的外壁为规则的圆，内壁为非规则的圆，内壁包括上弧面和下弧面，上弧面与外壁同心，下弧面不与外壁同心，下弧面上设有所述反光膜102，设有反光膜102的内壁侧的壁厚大于未设置反光膜102的内壁的壁厚，使得下弧面的曲率大于上弧面的曲率，此结构使得下弧面靠近所述光纤200的轴心，在下弧面上设有所述反光膜102，从护套结构的横截面看，所述护套101未覆盖反光膜102的部分的圆心角为180°，使得光纤200出射的激光最终汇聚成180°的范围出射，可以对目标病灶区域300进行180°范围的覆盖消融。
如图7所示，所述护套101的内壁和外部均为规则的圆，内壁面上设有所述反光膜102，从护套结构的横截面看，所述护套101未覆盖反光膜102的部分的圆心角为180°，使得光纤200出射的激光最终汇聚成180°的范围出射，可以对目标病灶区域300进行180°范围的覆盖消融。
形式三：如图8所示，所述护套101的外壁为规则的圆，内壁为非规则的圆，内壁包括上弧面和下弧面，上弧面与外壁同心，下弧面不与外壁同心，下弧面上设有所述反光膜102，设有反光膜102的内壁侧的壁厚大于未设置反光膜102的内壁的壁厚，使得下弧面的曲率大于上弧面的曲率，此结构使得下弧面靠近所述光纤200的轴心，在下弧面上设有所述反光膜102，从护套结构的横截面看，所述护套101未覆盖反光膜102的部分的圆心角大于180°，使得光纤200出射的激光最终汇聚成大于180°角度的范围出射，可以对目标病灶区域300进行更大范围的覆盖消融。
如图9所示，所述护套101的外壁和内壁均为规则的圆，在内壁面上设有所述反光膜102，从护套结构的横截面看，所述护套101未覆盖反光膜102的部分的圆心角大于180°，使得光纤200出射的激光最终汇聚成大于180°角度的范围出射，可以对目标病灶区域300进行更大范围的覆盖消融。
可理解地，在本实施例1中，所述护套101的横截面可以是规则的圆环，也可以是非规则的圆环，通过改变所述反光膜102的覆盖范围和/或相对于光纤200的位置能够得到不同的出光范围。优选护套101的横截面为规则的圆环，内壁设有反光膜102的形式。
实施例2
本发明的又一个具体实施例，如图10所示，公开了一种用于消融手术光纤的护套结构(以下简称“护套结构”)，与实施例1的不同之处在于，所述光路调节组件包括反光膜102和增透膜103，所述增透膜103设于反光膜102的相对侧，从而增加护套101的透光量，减少或消除杂散光，使得光纤200发出的激光尽量多的照射到目标病灶区域300进行消融。
本实施例中，通过增透膜103与反光膜102的结合使用，使得目标病灶区域300能够获得更多的激光，达到更佳的消融效果。其他结构和有益效果与实施例1的相同，在此不再一一赘述。
实施例3
本发明的又一个具体实施例，如图11-图12所示，公开了一种用于消融手术光纤的护套结构(以下简称“护套结构”)，护套结构包括护套101和光路调节组件，所述光路调节组件设于所述护套101的侧壁前端，所述光路调节组件能够改变位于所述护套101内的光纤200发出的激光的光路以对目标病灶区域300进行消融。
在该实施例3中，所述光路调节组件为透镜结构104，所述透镜结构104可以改变消融范围的大小和/或形状。因为所述透镜结构104的增加，把原来呈圆环状的消融区域转变为如图11、图12所示形状的消融区301，进而可以适配更多的不规则肿瘤。
所述透镜结构104位于护套101上，可理解地，透镜结构104既可以作为单独的部件设于护套101的内壁上，比如将透镜结构104粘贴在护套101的内壁上，也可以作为所述护套101的一部分。
本实施例中，为了减小护套结构的体积，所述透镜结构104和所述护套101是一体结构。当然也可以在所述护套101的侧壁上制作透镜结构104，所述透镜结构104嵌设在护套101的侧壁设置的槽内。
所述透镜结构104可以为聚光镜或发散镜，其中聚光镜优选为凸透镜，发散镜优选为凹透镜。
请再次参阅图11，所述透镜结构104为凸透镜，所述光纤200发出的激光周向发散，经过凸透镜后变为平行光出射，可以局部突出和/或加深对透镜结构104所在部位的目标病灶区域300的消融。
如图12所示，所述透镜结构104为凹透镜，所述光纤200发出的激光周向发散，经过凹透镜后变的更加发散，扩大透镜结构104所在位置出光的覆盖范围，增强消融效果。
本实施例提供的护套结构，在所述护套101上设有透镜结构104，透镜结构104具体设于护套101的侧壁前端，当光纤200用于消融手术时，通过设置于所述护套101上的透镜结构104改变光纤200发出的激光的路径，因此对形状不规则肿瘤的消融变得更为灵活和易于操作。
实施例4
本发明的又一个具体实施例，如图13-图20所示，公开了一种用于消融手术光纤的护套结构(以下简称“护套结构”)，护套结构包括护套101和光路调节组件，所述光路调节组件设于所述护套101的侧壁前端，所述光路调节组件能够改变位于所述护套101内的光纤200发出的激光的光路以对目标病灶区域300进行消融。
所述光路调节组件包括反光膜102和透镜结构104，所述反光膜102用于将所述光纤200出射的光线都导向目标病灶区域300的方向，以实现单方向的发射；所述反光膜102和所述透镜结构104配合可以适配更多不同形状的肿瘤。
所述反光膜102和透镜结构104相对设置，分别位于所述光纤200的两侧。如图13-图16所示，所述透镜结构104为凸透镜，光纤200周向发射的激光在遇到反光膜102时被平行返回至凸透镜后进行聚焦，加上光纤200直接透过凸透镜形成的平行光束，能够增 强对目标病灶区域300某一区域的消融。
如图17-图20所示，所述透镜结构104为凹透镜，光纤200周向发射的激光在遇到所述反光膜102后被平行返回至凹透镜，经过凹透镜折射后以更大的折射角散发，加上光纤200直接透过凹透镜折射的光束，能够增强对目标病灶区域300特定范围的消融。
可理解地，本实施例中，也可以改变反光膜102的覆盖面积及设有反光膜102处的弧形面的结构来获得不同的出光范围，如上文实施例1所示，在此不再赘述。
本发明在护套上设置光路调节组件来改变光纤的出光轨迹，通过本发明的护套结构，配合普通光纤便能够实现侧射出光的效果；且不同的光路调节组件可以配合组合使用，以更加多种不同的形式适配各种情况下的肿瘤，更好的适形消融。护套的工艺成本相对于特殊光纤要简单，便宜，更换更加方便。
本发明的多种形状的护套结构，实现了弥散光纤侧射出光；通过护套上做相应的反射层或者光学透镜结构，实现了弥散光纤的侧射出光，并可以按实际需求调整光的发散角及消融范围。
以上所述，仅为本发明较佳的具体实施方式，但本发明的保护范围并不局限于此，任何熟悉本技术领域的技术人员在本发明揭露的技术范围内，可轻易想到的变化或替换，都应涵盖在本发明的保护范围之内。

Claims (10)

  1. 一种用于消融手术光纤的护套结构，其特征在于，包括护套(101)和光路调节组件；所述光路调节组件设于所述护套(101)上，且能够改变位于所述护套(101)内的光纤(200)发出的激光的光路以对目标病灶区域(300)进行适形消融。
  2. 根据权利要求1所述的用于消融手术光纤的护套结构，其特征在于，所述光路调节组件为反光膜(102)，所述反光膜(102)设于所述护套(101)的侧壁上。
  3. 根据权利要求2所述的用于消融手术光纤的护套结构，其特征在于，所述反光膜(102)设于所述护套(101)的内侧壁上和/或外侧壁上。
  4. 根据权利要求2所述的用于消融手术光纤的护套结构，其特征在于，通过改变所述反光膜(102)沿所述护套(101)的侧壁周向的覆盖范围和/或改变所述反光膜(102)所在所述护套(101)的侧壁的形状能够改变所述护套(101)的出射光范围。
  5. 根据权利要求1-4任一所述的用于消融手术光纤的护套结构，其特征在于，所述护套(101)为细长的管状结构。
  6. 根据权利要求5所述的用于消融手术光纤的护套结构，其特征在于，所述护套(101)的横截面形状为规则或非规则的圆环。
  7. 根据权利要求2所述的用于消融手术光纤的护套结构，其特征在于，所述光路调节组件还包括增透膜(103)，所述增透膜(103)设于所述反光膜(102)的相对侧。
  8. 根据权利要求1所述的用于消融手术光纤的护套结构，其特征在于，所述光路调节组件为透镜结构(104)，所述透镜结构(104)位于所述护套(101)的侧壁面上。
  9. 根据权利要求2所述的用于消融手术光纤的护套结构，其特征在于，所述光路调节组件还包括透镜结构(104)，所述反光膜(102)和所述透镜结构(104)分别位于所述光纤(200)的两侧。
  10. 根据权利要求8或9所述的用于消融手术光纤的护套结构，其特征在于，所述透镜结构(104)为聚光镜或发散镜。
PCT/CN2022/122499 2021-09-30 2022-09-29 一种用于消融手术光纤的护套结构 WO2023051672A1 (zh)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
CN202111165503.0 2021-09-30
CN202111165503.0A CN113855228B (zh) 2021-09-30 2021-09-30 一种用于消融手术光纤的护套结构

Publications (1)

Publication Number Publication Date
WO2023051672A1 true WO2023051672A1 (zh) 2023-04-06

Family

ID=79001510

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2022/122499 WO2023051672A1 (zh) 2021-09-30 2022-09-29 一种用于消融手术光纤的护套结构

Country Status (2)

Country Link
CN (1) CN113855228B (zh)
WO (1) WO2023051672A1 (zh)

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN113855228B (zh) * 2021-09-30 2023-12-01 杭州佳量医疗科技有限公司 一种用于消融手术光纤的护套结构

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040167503A1 (en) * 1999-08-25 2004-08-26 Cardiofocus, Inc. Malleable surgical ablation instruments
US20070208329A1 (en) * 2004-12-10 2007-09-06 Jim Ward Ablative treatment of atrial fibrillation via the coronary sinus
CN113409286A (zh) * 2021-06-28 2021-09-17 杭州佳量医疗科技有限公司 一种基于磁共振引导的激光消融评估系统
CN113855228A (zh) * 2021-09-30 2021-12-31 杭州佳量医疗科技有限公司 一种用于消融手术光纤的护套结构
CN113995508A (zh) * 2021-11-05 2022-02-01 杭州佳量医疗科技有限公司 一种医用光纤导向结构及导向方法
CN215994233U (zh) * 2021-09-30 2022-03-11 杭州佳量医疗科技有限公司 一种光路可调的消融管
CN216455275U (zh) * 2021-11-05 2022-05-10 杭州佳量医疗科技有限公司 一种用于手术消融器件的导向结构

Family Cites Families (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AU678342B2 (en) * 1992-06-12 1997-05-29 Pdt Systems, Inc. Cylindrical diffusion tips for optical fibers and method for making
US6013053A (en) * 1996-05-17 2000-01-11 Qlt Photo Therapeutics Inc. Balloon catheter for photodynamic therapy
US8105322B2 (en) * 2008-03-11 2012-01-31 Shaser, Inc. Replacement cartridges for light-based dermatologic treatment devices
CN101557257A (zh) * 2009-04-23 2009-10-14 上海交通大学 光纤瑞利散射信号探测器
CN102688095B (zh) * 2012-06-15 2014-08-27 上海安通医疗科技有限公司 肾动脉激光消融导管
CN204116644U (zh) * 2014-08-29 2015-01-21 刘鹤 侧出光透镜光纤
CN204144665U (zh) * 2014-09-10 2015-02-04 山东省药物研究院 一种医用532nm绿激光发生装置
WO2017011587A1 (en) * 2015-07-13 2017-01-19 Avinger, Inc. Micro-molded anamorphic reflector lens for image guided therapeutic/diagnostic catheters
CN107242904B (zh) * 2017-07-19 2023-06-20 重庆半岛医疗科技有限公司 一种光束均化的治疗装置
CN108245126A (zh) * 2018-03-26 2018-07-06 精微视达医疗科技（武汉）有限公司 一种可以激光消融的探头式共聚焦显微内窥镜
CN209361672U (zh) * 2018-05-14 2019-09-10 广州市普东医疗设备股份有限公司 一种可激发自体荧光的激光前列腺治疗系统
WO2020008398A1 (en) * 2018-07-03 2020-01-09 Andritz Ag Laser apparatus and method
CN111110346B (zh) * 2019-12-31 2021-03-09 华科精准（北京）医疗科技有限公司 用于激光间质热疗系统的装置
CN212973069U (zh) * 2021-03-18 2021-04-16 常州纵慧芯光半导体科技有限公司 一种激光美容仪

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040167503A1 (en) * 1999-08-25 2004-08-26 Cardiofocus, Inc. Malleable surgical ablation instruments
US20070208329A1 (en) * 2004-12-10 2007-09-06 Jim Ward Ablative treatment of atrial fibrillation via the coronary sinus
CN113409286A (zh) * 2021-06-28 2021-09-17 杭州佳量医疗科技有限公司 一种基于磁共振引导的激光消融评估系统
CN113855228A (zh) * 2021-09-30 2021-12-31 杭州佳量医疗科技有限公司 一种用于消融手术光纤的护套结构
CN215994233U (zh) * 2021-09-30 2022-03-11 杭州佳量医疗科技有限公司 一种光路可调的消融管
CN113995508A (zh) * 2021-11-05 2022-02-01 杭州佳量医疗科技有限公司 一种医用光纤导向结构及导向方法
CN216455275U (zh) * 2021-11-05 2022-05-10 杭州佳量医疗科技有限公司 一种用于手术消融器件的导向结构

Also Published As

Publication number Publication date
CN113855228A (zh) 2021-12-31
CN113855228B (zh) 2023-12-01

Similar Documents

Publication Publication Date Title
CN102740928B (zh) 绞扭器纤维光学系统及其在医学应用中的用途
JP3073994B2 (ja) 放射角度可変レーザー照射装置
US10092356B2 (en) Radial emissions from optical fibers
US11324553B2 (en) Side fire optical fiber for high power applications
WO2023051672A1 (zh) 一种用于消融手术光纤的护套结构
JP2004503326A (ja) 心臓用の光切除器具
US8827991B2 (en) Medical laser treatment device and method utilizing total reflection induced by radiation
JPH0747081A (ja) レーザを用いた経尿道前立腺切除装置
JPH0394744A (ja) レーザ光の照射装置
EP0020749A1 (en) Excising pathological tissue using a beam of radiation
JPH02213804A (ja) レーザ光出射装置
KR20080068730A (ko) 수술용 광각 조명기
CN217467338U (zh) 内窥镜探头
WO2023078168A1 (zh) 一种医用光纤导向结构及导向方法
CN108175499A (zh) 一种双波长激光手术装置
CN215994233U (zh) 一种光路可调的消融管
US20110166562A1 (en) High Durability Side Fire Optical Fiber for High Power Applications
JP4388647B2 (ja) レーザ照射装置
KR20110091295A (ko) 다방면 조사 광섬유 프로브 및 이를 위한 제조방법
CN108709623A (zh) 光声透镜的制作方法、聚焦超声器件及聚焦超声量测系统
CN109283688B (zh) 一种反射型匀光器以及其制备和应用
US5658275A (en) Surgical laser instrument
JPH11276499A (ja) レーザ照射装置
KR102439098B1 (ko) 수술용 기구
WO2020093616A1 (zh) 一种匀出光的光纤穿刺针及狭缝和匀光器的制备方法

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 22875055

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE