CN215994233U - Ablation tube with adjustable light path - Google Patents

Abstract

The utility model relates to an optical path adjustable ablation tube belongs to medical instrument technical field, has solved among the prior art problem that optic fibre can't carry out accurate conformal ablation to the tumour. The utility model comprises a sheath and a light path adjusting component, wherein the optical fiber is positioned in the lumen of the sheath; the optical path adjusting component is integrally and/or detachably arranged on the sheath, and the optical path adjusting component can change the optical path of laser emitted by the optical fiber so as to carry out conformal ablation on a target lesion area. The utility model discloses can carry out accurate conformal ablation to target focus region.

Description

Ablation tube with adjustable light path

Technical Field

The utility model relates to the technical field of medical equipment, especially, relate to an optical path adjustable ablation tube.

Background

In recent years, laser interstitial thermotherapy guided by magnetic resonance imaging shows wide clinical application value in the aspect of treating tumors. This technique, which utilizes the heat released by the laser to ablate the diseased tissue, is considered to be a less invasive procedure than open procedures. However, the ablation operation has the outstanding disadvantages that: precise conformal ablation is difficult to achieve. Clinically known tumors have various shapes, including polyps, papilla, nodular, lobular, cystic, diffuse hypertrophy, ulcers, and infiltrative masses. Accurate conformal ablation of tumors of various shapes is required, and accurate and error-free surgical planning is required, for example, one or more surgical channels are provided for a specific tumor shape, and then ablation is performed by using one or more optical fibers of different types at a time; and secondly, the laser energy is flexibly regulated and controlled.

At present, optical fiber is generally used as a transmission medium of laser, and the light emitting range and direction of the optical path are determined by the type of the optical fiber. In laser ablation, three types of optical fibers, namely a dispersion optical fiber, a ring optical fiber and a side-emitting optical fiber, are commonly used. The three types of optical fibers have different light-emitting ranges, for example, the front end light-emitting mode of the annular optical fiber is output along the radial direction and the whole circumference; the light outgoing mode of the front end of the dispersion optical fiber is output along the radial direction and the axial direction according to the predefined length and the whole circumference; the front light-emitting mode of the side-emitting optical fiber is output along the radial side surface.

Therefore, in order to achieve precise conformal ablation, the light emitting direction and/or light emitting range of the operator should be adjusted flexibly according to the preoperative plan and the tumor shape as much as possible during the laser ablation operation. However, laser ablation operation is not widely implemented at home at present, and there are few ablation optical fiber sheaths or similar products on the market that can flexibly regulate and control the light emitting direction and/or the light emitting range again under a given optical fiber model.

SUMMERY OF THE UTILITY MODEL

In view of the foregoing analysis, embodiments of the present invention provide an ablation tube with an adjustable optical path, so as to solve the problem that the existing optical fiber cannot perform precise conformal ablation on a tumor.

The utility model provides an ablation tube with an adjustable light path, which comprises a sheath and a light path adjusting component, wherein an optical fiber is positioned in a tube cavity of the sheath;

the optical path adjusting component is integrally and/or detachably arranged on the sheath, and the optical path adjusting component can change the optical path of laser emitted by the optical fiber so as to carry out conformal ablation on a target lesion area.

Further, the light path adjusting component is a reflective film, and the reflective film is arranged on the side wall of the sheath.

Further, the reflective film is arranged on the inner side wall and/or the outer side wall of the sheath.

Further, the central angle of the part of the sheath, which is not covered by the reflective film, ranges from 0 to 360 degrees.

Further, the sheath is an elongated tubular structure, and the cross-sectional shape of the sheath is a regular or irregular circular ring.

Further, the light path adjusting assembly further comprises an antireflection film, and the antireflection film is arranged on the opposite side of the reflecting film.

Further, the optical path adjusting component is a lens structure, and the lens structure is located on the side wall surface of the sheath.

Further, the optical path adjusting assembly further comprises a lens structure, and the reflective film and the lens structure are respectively located on two sides of the optical fiber.

Further, the lens structure is a condenser lens.

Further, the lens structure is a diverging mirror.

Compared with the prior art, the utility model discloses can realize one of following beneficial effect at least:

(1) the utility model discloses be equipped with the light path adjusting part on the sheath, when optic fibre was used for melting the operation, changed the route of the laser that optic fibre sent through the light path adjusting part who sets up on the sheath, can make laser accomplish and melt the regional tumour of target focus, need not consider the influence of tumour position, shape and size, avoided technical difficulty, the cost-push and the inconvenient scheduling problem of operation brought in order to avoid the hindrance on the passageway.

(2) The utility model realizes the side light emission of the dispersive optical fiber by the ablation tube with various shapes; by manufacturing a corresponding reflecting layer or an optical lens structure on the sheath, side-emitting light of the dispersion optical fiber is realized, and the divergence angle and the ablation range of the light can be adjusted secondarily according to actual requirements.

The utility model discloses in, can also make up each other between the above-mentioned each technical scheme to realize more preferred combination scheme. Additional features and advantages of the invention will be set forth in the description which follows, and in part will be obvious from the description, or may be learned by practice of the invention. The objectives and other advantages of the invention will be realized and attained by the structure particularly pointed out in the written description and drawings.

Drawings

The drawings are only for purposes of illustrating particular embodiments and are not to be construed as limiting the invention, wherein like reference numerals are used to designate like parts throughout the drawings.

FIG. 1 is a schematic view of an ablation catheter of a particular embodiment;

FIG. 2 is a schematic cross-sectional view (one) of the ablation tube of embodiment 1;

FIG. 3 is a schematic cross-sectional view of the ablation tube of embodiment 1;

FIG. 4 is a schematic cross-sectional view (III) of the ablation tube of embodiment 1;

FIG. 5 is a schematic cross-sectional view (IV) of the ablation tube of example 1;

FIG. 6 is a schematic cross-sectional view (V) of the ablation tube of embodiment 1;

FIG. 7 is a schematic cross-sectional View (VI) of the ablation tube of example 1;

FIG. 8 is a schematic cross-sectional View (VII) of the ablation tube of specific embodiment 1;

FIG. 9 is a schematic cross-sectional view (eight) of the ablation tube of embodiment 1;

FIG. 10 is an illustration of the ablation catheter of specific embodiment 2;

FIG. 11 is a schematic view (one) of the ablation catheter of embodiment 3;

FIG. 12 is a schematic view of an ablation catheter of example 3;

FIG. 13 is a schematic cross-sectional view (one) of the ablation tube of example 4;

FIG. 14 is a schematic cross-sectional view of the ablation tube of example 4 (II);

FIG. 15 is a schematic cross-sectional view (III) of the ablation tube of example 4;

FIG. 16 is a schematic cross-sectional view (IV) of the ablation tube of example 4;

FIG. 17 is a schematic cross-sectional view (V) of the ablation tube of example 4;

FIG. 18 is a schematic cross-sectional View (VI) of the ablation tube of example 4;

FIG. 19 is a schematic cross-sectional View (VII) of the ablation tube of specific embodiment 4;

fig. 20 is a schematic cross-sectional view (eight) of the ablation tube of embodiment 4.

Reference numerals:

101-a sheath; 102-a light-reflecting film; 103-an antireflection film; 104-a lens structure;

200-an optical fiber; 300-target lesion area; 301-ablation zone.

Detailed Description

The following detailed description of the preferred embodiments of the invention, which is to be read in connection with the accompanying drawings, forms a part of the invention, and together with the embodiments of the invention, serve to explain the principles of the invention and not to limit the scope of the invention.

In the description of the embodiments of the present invention, it should be noted that, unless explicitly stated or limited otherwise, the term "connected" should be interpreted broadly, and may be, for example, fixedly connected, detachably connected, or integrally connected, mechanically connected, electrically connected, directly connected, or indirectly connected through an intermediate medium. The specific meaning of the above terms in the present invention can be understood according to specific situations by those skilled in the art.

The terms "top," "bottom," "above … …," "below," and "on … …" as used throughout the description are relative positions with respect to components of the device, such as the relative positions of the top and bottom substrates inside the device. It will be appreciated that the devices are multifunctional, regardless of their orientation in space.

Based on the purpose of improving the light-emitting direction and light-emitting range of the ablation optical fiber to irradiate laser to a focus flexibly, controllably and precisely in a conformal manner, an author carries out multidirectional adjustment on an invasive surgical instrument for ablation on the basis of the prior art and the defects, and the ablation optical fiber is taken as an example for explanation: 1. the optical fiber for ablation is not required to be further optimally designed, so that the process problem of optical fiber manufacturing is avoided, and the development cost is reduced; 2. the existing optical fiber and the ablation tube are relatively fixed, and the control of the focus ablation range and the control of the light emitting direction only depend on the wavelength of the laser source and the type of the optical fiber. That is, on the basis of selecting a certain optical fiber model, the light path irradiated on the lesion is uniquely determined, and during the operation, the optical fiber can only be axially moved or rotated to change the light transmission direction, but the axial movement or the rotation will cause the coupling efficiency of the optical fiber to be lower, thereby affecting the ablation result. And this application disposes the light path and adjusts the subassembly on the optic fibre sheath (not optic fibre itself), has realized adjusting many times to the laser light path to directly carry out axial displacement or rotatory mechanical action to optic fibre has been avoided, under the prerequisite of having guaranteed good light-emitting, can accomplish again to the accurate conformal ablation of focus, further improved the utilization ratio of the light energy that melts.

To this end, the present invention provides an ablation tube (hereinafter referred to as "ablation tube") with an adjustable optical path, as shown in fig. 1-20, the ablation tube includes a sheath 101, the sheath 101 is a slender tubular structure, and an optical fiber 200 is located in a lumen of the sheath 101. The optical path adjusting component is integrally and/or separately configured on the sheath 101. The optical path adjustment assembly is capable of altering the laser path emitted by the optical fiber 200 positioned within the sheath 101 for precise conformal ablation of the targeted lesion area 300.

Compared with the prior art, the ablation tube that this embodiment provided is equipped with the light path adjusting part on the sheath, when optic fibre was used for ablating the operation, through set up in the laser transmission route that the light path adjusting part on the sheath changed or the secondary changes optic fibre sent can accomplish the conformal ablation to the tumour in the target focus area under the condition of not considering tumour position, shape and size, and then makes the preoperative planning of laser ablation operation become simple swift. Meanwhile, the injury to the upper important tissue near the operation channel can be flexibly avoided by the irregularity of the ablation range caused by the change of the optical path transmission by the optical path adjusting component.

In a preferred embodiment, the sheath 101 has a certain hardness, the material of the sheath is preferably PC (Polycarbonate) plastic, and the sheath 101 has a function of protecting the optical fiber 200 and isolating the optical fiber 200 from directly contacting with the tissue, so as to prevent the optical fiber 200 from damaging the tissue of the human body. Considering that the sheath 101 needs to extend into the human tissue, and the optical fiber 200 disposed therein is used to ablate the cancer cells in the target lesion area 300, the front end of the sheath 101 is provided with a certain taper, which can function as an ablation channel for the optical fiber 200. The optical path adjusting component is arranged on the side wall of the sheath 101. Since the light exit position of the optical fiber 200 is the front end of the optical fiber 200, the optical path adjusting component is disposed near the front end of the sheath 101, that is, the optical path adjusting component is disposed corresponding to the light exit position of the optical fiber 200.

By arranging the light path adjusting component capable of changing the light path for multiple times on the side wall of the sheath 101, the laser transmission path emitted by the optical fiber 200 is adjusted as required, and the adjusted laser path can carry out conformal ablation on the target lesion area 300 more specifically. In addition, compared with the manufacturing process of the optical fiber, the structural design and the manufacturing of the sheath are easier, so that the ablation tube of the ablation optical fiber in various forms can be manufactured, wider selectivity is provided for an operator, and the laser ablation operation is simpler. The brain tumor will be taken as an example and the laser ablation technology will be integrated to make a detailed explanation of the present invention.

Example 1

The utility model discloses a specific embodiment, as shown in fig. 1 and fig. 9, discloses a light path adjustable ablation tube (hereinafter referred to as "ablation tube"), ablation tube includes sheath 101 and light path adjusting part, light path adjusting part locates the lateral wall front end of sheath 101, light path adjusting part can change the light path of the laser that is located fiber 200 in the sheath 101 is sent out and is ablated target focus area 300. In fig. 2 to 9, 11 to 12, 14, 16, 18, and 20, an ablation region 301 is an ablation region that can be covered by the light emitted from the ablation tube.

Referring to fig. 1 again, in this embodiment 1, the optical path adjusting element is a reflective film 102, the reflective film 102 is disposed on the sidewall of the sheath 101, and the reflective film 102 can change incident light into parallel light and emit the parallel light. In particular, the reflective film 102 is glued to the wall of the sheath 101.

The reflective film 102 has a covering length along the axial direction of the sheath 101 and a covering width along the circumferential direction of the sheath 101 on the sheath 101, and the following covering refers to the covering range of the reflective film 102 along the circumferential direction of the sheath 101.

As shown in fig. 1-4 and 6-9, the reflective film 102 may be disposed on an inner wall of the sheath 101, and considering that the reflective film 102 may reflect with the inner wall to consume a part of energy when the reflective film 102 is on the outer wall, disposing the reflective film 102 on the inner wall may avoid energy loss of the laser, and ensure efficiency of the laser; as shown in fig. 5, the reflective film 102 may also be disposed on the outer wall of the sheath 101, so that the reflective film 102 is disposed on the outer wall for easier operation. Preferably, the reflective film 102 is disposed on the inner wall of the sheath 101. The light emitting film 102 is disposed on the inner wall or the outer wall, and has the same adjusting effect on the light path.

It should be noted that, in other embodiments, the reflective film 102 may also be disposed on the inner wall of the sheath 101 or the outer wall of the sheath 101, and in other embodiments, description is not repeated.

It should be noted that the reflective film 102 may be disposed on both the inner wall and the outer wall of the sheath 101, and in this structure, since the reflective film 102 on the inner wall and the outer wall of the overlapping region does not work, the reflective film 102 disposed on the inner wall and the reflective film 102 disposed on the outer wall are selected according to the requirement.

Since the optical fiber 200 is disposed in the sheath 101, when the fiber tip of the optical fiber 200 emits laser light, the laser light irradiates the reflective film 102 and is then emitted as parallel light, so that the laser light emitted from the optical fiber 200 can be focused toward the opposite direction of the reflective film 102 for ablating the target lesion area 300 in the direction. On one hand, due to the emission of the parallel light, the uniformity of the emitted light is further enhanced, and the more uniform the light energy irradiated on the target lesion area 300 is; on the other hand, the reflective film 102 secondarily changes the transmission path of the light path, so that all the light paths are emitted towards the same direction, the damage strength of the light energy is increased, and the ablation range of the target focus area 300 is expanded under the condition that the laser power is not changed.

Preferably, the optical fiber 200 may be an annular optical fiber or a dispersive optical fiber, that is, when the optical fiber 200 is circumferentially emitted, the reflective film 102 is disposed at any position of the front end of the inner wall of the sheath 101, the laser light emitted from the optical fiber 200 is directly emitted at a portion where the reflective film 102 is not disposed, and the laser light emitted from the optical fiber 200 is reflected back at a position where the reflective film 102 is disposed, and is converged with the directly emitted laser light to the target lesion area 300.

In this embodiment 1, the light emitting film 102 is disposed on the inner wall of the sheath 101, and the light emitted from the optical fiber 200 is guided to the direction of the target lesion area 300, so as to realize the emission of the laser light along the single side direction of the optical fiber 20, and thus the ablation can be performed on the target lesion area 300 at a specific site. At this time, the dispersive optical fiber can also realize side light emission by matching with the sheath.

Understandably, since the inner wall of the sheath 101 is an arc-shaped surface, the area covered by the reflective film 102 on the inner wall of the sheath 101 and the shape of the arc-shaped surface will affect the path of the reflected light. That is, the covering 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-emitting ranges, so as to satisfy the ablation of different ranges and different directions of the target lesion area 300.

Different light emitting ranges can be obtained by changing the inner wall structure of the sheath 101 at the side provided with the reflective film 102 and the position of the optical fiber 200 relative to the reflective film 102, so that important tissues such as blood vessels, hippocampus and the like can be avoided. Only 3 forms of ablation tubes are listed below.

The first form: as shown in fig. 2, the cross section of the sheath 101 is an irregular ring (the inner wall and the outer wall of the sheath 101 are both irregular circles), and includes an upper semicircular ring and a lower semicircular ring, the upper semicircular ring is not provided with the reflective film 102, the inner wall of the lower semicircular ring is provided with the reflective film 102, the curvature of the lower semicircular ring is greater than that of the upper semicircular ring, and the lower semicircular ring is close to the axis of the optical fiber 200, the inner wall arc surface of the lower semicircular ring is more gentle than that of the upper semicircular ring, the reflective film 102 is provided on the gentle inner wall, the central angle of the part of the sheath 101 not covered by the reflective film 102 (the included angle between the light-emitting range boundary 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 is finally converged into a small-range emergent angle, such as a right angle or an acute angle.

In this embodiment, the reflective film 102 is arranged on the gentle inner wall of the sheath 101, and when viewed from the cross section of the ablation tube, the central angle of the portion of the sheath 101 not covered by the reflective film 102 is not greater than 90 °, so that the laser emitted by the optical fiber 200 is emitted in a smaller angle range to ablate the target lesion area 300, and the range which can be covered by the emitted light is the ablation area 301.

As shown in fig. 3, the cross section of the sheath 101 is an irregular circular ring (the inner wall of the sheath 101 is an irregular circle, and the outer wall is a regular circle), the reflective film 102 is disposed on the inner wall of the sheath 101, the central angle of the portion 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 emitted by the optical fiber 200 is finally converged into a small range of exit angle, such as an acute angle, to ablate the target lesion area 300.

As shown in fig. 4, the cross section of the sheath 101 is a regular circular ring (both the inner wall and the outer wall of the sheath 101 are regular circles), the reflective film 102 is disposed on the inner wall of the sheath 101, and the central angle of the portion of the sheath 101 not covered by 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 exit angles, such as a right angle or an acute angle.

As shown in fig. 5, the cross section of the sheath 101 is a regular circular ring (both the inner wall and the outer wall of the sheath 101 are regular circles), the reflective film 102 is disposed on the outer wall of the sheath 101, and the central angle of the portion of the sheath 101 not covered by 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 exit angles, such as a right angle or an acute angle. It can be understood that the reflective film 102 is disposed on the outer wall of the sheath 101 (see fig. 2-4) with other cross-sectional structures to achieve the same effect, and the description thereof is omitted here.

It can be understood that the central angle of the portion not covered by the reflective film 102 can be changed within 90-180 degrees by changing the coverage of the reflective film 102 on the sheath 101.

The second form: as shown in fig. 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, the lower arc surface is not concentric with the outer wall, the reflective film 102 is arranged on the lower arc surface, the wall thickness of the inner wall side provided with the reflective film 102 is greater than the wall thickness of the inner wall not provided with the reflective film 102, so that the curvature of the lower arc surface is greater than the curvature of the upper arc surface, the lower arc surface is close to the axis of the optical fiber 200, the reflective film 102 is arranged on the lower arc surface, and when viewed from the cross section of the ablation tube, the central angle of the portion of the sheath 101 not covered with the reflective film 102 is 180 °, so that the laser emitted from the optical fiber 200 finally converges to emit in a range of 180 °, and the coverage ablation of the target lesion area 300 can be performed in a range of 180 °.

As shown in fig. 7, the inner wall and the outer portion of the sheath 101 are both regular circles, the inner wall surface is provided with the reflective film 102, and when viewed from the cross section of the ablation tube, the central angle of the portion of the sheath 101 not covered by the reflective film 102 is 180 °, so that laser emitted from the optical fiber 200 is finally converged into a range of 180 ° and emitted, and the coverage ablation of the target lesion area 300 can be performed in a range of 180 °.

The third form: as shown in fig. 8, 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, the lower arc surface is not concentric with the outer wall, the reflective film 102 is arranged on the lower arc surface, the wall thickness of the inner wall side provided with the reflective film 102 is greater than the wall thickness of the inner wall not provided with the reflective film 102, so that the curvature of the lower arc surface is greater than the curvature of the upper arc surface, the lower arc surface is close to the axis of the optical fiber 200, the reflective film 102 is arranged on the lower arc surface, and when viewed from the cross section of the ablation tube, the central angle of the portion of the sheath 101 not covered with the reflective film 102 is greater than 180 °, so that the laser emitted from the optical fiber 200 finally converges to emit in a range greater than 180 °, and the target lesion area 300 can be ablated in a larger range.

As shown in fig. 9, the outer wall and the inner wall of the sheath 101 are both regular circles, the reflective film 102 is disposed on the inner wall, and when viewed from the cross section of the ablation tube, the central angle of the portion of the sheath 101 not covered by the reflective film 102 is greater than 180 °, so that the laser emitted from the optical fiber 200 is finally converged into a range of an angle greater than 180 ° and emitted, and the target lesion area 300 can be ablated in a wider range.

Understandably, in this embodiment 1, the cross section of the sheath 101 may be a regular circular ring or an irregular circular ring, and different light emitting ranges can be obtained by changing the coverage range of the reflective film 102 and/or the position relative to the optical fiber 200. The sheath 101 is preferably a regular circular ring in cross-section, with the inner wall being in the form of a reflective membrane 102.

Example 2

The utility model discloses a further specific embodiment, as shown in fig. 10, discloses an ablation tube (hereinafter referred to as "ablation tube") with adjustable light path, and the difference with embodiment 1 is that the light path adjusting component includes reflective membrane 102 and antireflection film 103, antireflection film 103 is located the opposite side of reflective membrane 102 to increase the light transmission of sheath 101, reduce or eliminate stray light, make the laser that optic fibre 200 sent shine target focus area 300 as much as possible and ablate.

In this embodiment, the antireflection film 103 and the reflective film 102 are used in combination, so that the target lesion area 300 can obtain more laser light, and a better ablation effect is achieved. Other structures and advantageous effects are the same as those of embodiment 1, and are not described in detail herein.

Example 3

Another embodiment of the present invention, as shown in fig. 11-12, discloses an ablation tube with adjustable optical path (hereinafter referred to as "ablation tube"), which comprises a sheath 101 and an optical path adjusting component, the optical path adjusting component is disposed at the front end of the side wall of the sheath 101, and the optical path adjusting component can change the optical path of the laser emitted from the optical fiber 200 located in the sheath 101 to ablate the target lesion area 300.

In this embodiment 3, the optical path adjusting component is a lens structure 104, and the lens structure 104 can change the size and/or shape of the ablation region. Due to the addition of the lens structure 104, the ablation region which is originally in a circular ring shape is converted into the ablation region 301 which is in the shape shown in fig. 11 and 12, so that the irregular tumor can be adapted to more.

The lens structure 104 is disposed on the sheath 101. it is understood that the lens structure 104 can be disposed on the inner wall of the sheath 101 as a separate component, such as by adhering the lens structure 104 to the inner wall of the sheath 101, or can be a part of the sheath 101.

In this embodiment, the lens structure 104 and the sheath 101 are a unitary structure in order to reduce the volume of the ablation tube. Of course, the lens structure 104 may also be formed on the sidewall of the sheath 101, and the lens structure 104 is embedded in a groove formed on the sidewall of the sheath 101.

The lens structure 104 may be a condenser lens, which is preferably a convex lens, or a diverging lens, which is preferably a concave lens.

Referring to fig. 11 again, the lens structure 104 is a convex lens, and the laser emitted from the optical fiber 200 is circumferentially diffused and then changed into parallel light to be emitted through the convex lens, so as to locally protrude and/or deepen ablation of the target lesion area 300 at the position of the lens structure 104.

As shown in fig. 12, the lens structure 104 is a concave lens, and the laser emitted from the optical fiber 200 is circumferentially dispersed and becomes more dispersed after passing through the concave lens, so as to expand the coverage of the light emitted from the position of the lens structure 104 and enhance the ablation effect.

In the ablation tube provided by the embodiment, the lens structure 104 is arranged on the sheath 101, and the lens structure 104 is specifically arranged at the front end of the side wall of the sheath 101, so that when the optical fiber 200 is used for an ablation operation, the path of the laser emitted by the optical fiber 200 is changed through the lens structure 104 arranged on the sheath 101, and thus, the ablation of the tumor with irregular shape becomes more flexible and easier to operate.

Example 4

In another embodiment of the present invention, as shown in fig. 13-20, an ablation tube with an adjustable optical path (hereinafter referred to as "ablation tube") is disclosed, which comprises a sheath 101 and an optical path adjusting component, the optical path adjusting component is disposed at the front end of the side wall of the sheath 101, and the optical path adjusting component can change the optical path of the laser emitted from the optical fiber 200 inside the sheath 101 to ablate the target lesion area 300.

The light path adjusting component comprises a reflective membrane 102 and a lens structure 104, wherein the reflective membrane 102 is used for guiding 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 membrane 102 and the lens structure 104 cooperate to accommodate more tumors of different shapes.

The reflective film 102 and the lens structure 104 are disposed opposite to each other and located on two sides of the optical fiber 200. As shown in fig. 13-16, the lens structure 104 is a convex lens, the laser light emitted from the circumferential direction of the optical fiber 200 is focused after being parallel and returned to the convex lens when encountering the reflective film 102, and the optical fiber 200 directly transmits the parallel light beam formed by the convex lens, so as to enhance the ablation of a certain region of the target lesion area 300.

As shown in fig. 17-20, the lens structure 104 is a concave lens, and the laser emitted from the circumferential direction of the optical fiber 200 is parallel returned to the concave lens after encountering the reflective film 102, and is refracted by the concave lens and then emitted at a larger refraction angle, and the optical fiber 200 directly penetrates through the light beam refracted by the concave lens, so that the ablation of the target lesion area 300 in a specific range can be enhanced.

It is understood that in this embodiment, the coverage area of the reflective film 102 and the structure of the arc-shaped surface where the reflective film 102 is disposed may also be changed to obtain different light-emitting ranges, as shown in embodiment 1, which is not described herein again.

The utility model arranges the light path adjusting component on the sheath to change the light-emitting track of the optical fiber, and the ablation tube can realize the side-emitting light effect by matching with the common optical fiber; and different light path adjusting components can be matched and combined for use, so that the device can be adapted to tumors under various conditions in more various different forms, and better conformal ablation is realized. The process cost of the sheath is simple and cheap relative to the special optical fiber, and the sheath is more convenient to replace.

The utility model realizes the side light emission of the dispersive optical fiber by the ablation tube with various shapes; by manufacturing a corresponding reflecting layer or an optical lens structure on the sheath, side-emitting light of the dispersion optical fiber is realized, and the divergence angle and the ablation range of the light can be adjusted according to actual requirements.

The above description is only for the preferred embodiment of the present invention, but the scope of the present invention is not limited thereto, and any changes or substitutions that can be easily conceived by those skilled in the art within the technical scope of the present invention should be covered by the present invention.

Claims (10)

1. An ablation tube with an adjustable light path is characterized by comprising a sheath (101) and a light path adjusting component, wherein an optical fiber (200) is positioned in a lumen of the sheath (101);

the optical path adjusting component is integrally and/or separately arranged on the sheath (101), and the optical path adjusting component can change the optical path of the laser emitted by the optical fiber (200) to perform conformal ablation on a target lesion area (300).

2. The ablation tube with adjustable optical path according to claim 1, wherein the optical path adjusting component is a reflective film (102), and the reflective film (102) is disposed on a side wall of the sheath (101).

3. The ablation tube with adjustable optical path according to claim 2, characterized in that the reflective film (102) is disposed on the inner sidewall and/or the outer sidewall of the sheath (101).

4. The ablation tube with the adjustable optical path according to claim 2, wherein the central angle of the portion of the sheath (101) not covered by the reflective film (102) ranges from 0 ° to 360 °.

5. The ablation tube with adjustable optical path according to any one of claims 1 to 4, characterized in that the sheath (101) is an elongated tubular structure, and the cross-sectional shape of the sheath (101) is a regular or irregular circular ring.

6. The ablation tube with the adjustable optical path according to claim 2, wherein the optical path adjusting assembly further comprises an antireflection film (103), and the antireflection film (103) is disposed on the opposite side of the reflective film (102).

7. The ablation tube with adjustable optical path according to claim 1, wherein the optical path adjusting component is a lens structure (104), and the lens structure (104) is located on a side wall surface of the sheath (101).

8. The ablation tube with adjustable optical path according to claim 2, wherein the optical path adjusting assembly further comprises a lens structure (104), and the reflective film (102) and the lens structure (104) are respectively located at two sides of the optical fiber (200).

9. The ablation tube with adjustable optical path according to claim 7 or 8, characterized in that the lens structure (104) is a condenser lens.

10. The ablation tube with adjustable optical path according to claim 7 or 8, characterized in that the lens structure (104) is a diverging mirror.

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