CN116407747A - Particle support - Google Patents
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- CN116407747A CN116407747A CN202111673762.4A CN202111673762A CN116407747A CN 116407747 A CN116407747 A CN 116407747A CN 202111673762 A CN202111673762 A CN 202111673762A CN 116407747 A CN116407747 A CN 116407747A
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- 239000002245 particle Substances 0.000 title claims abstract description 70
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
- A61N5/1002—Intraluminal radiation therapy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
- A61N5/1007—Arrangements or means for the introduction of sources into the body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N2005/1092—Details
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- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Pathology (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Radiology & Medical Imaging (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Prostheses (AREA)
Abstract
The invention relates to a particle scaffold for placement within a tissue tract, comprising: the support body, support body can elasticity support in the pipe wall of tissue pipeline, the support body is including being used for holding the hollow pipe of radioactive substance, the outer peripheral face of hollow pipe is provided with along the radial sunken recess of hollow pipe. The particle bracket has small shaping resistance in the shaping process, and can reduce shaping difficulty.
Description
Technical Field
The invention relates to the technical field of interventional medical instruments, in particular to a particle bracket.
Background
In recent years, the incidence of cancer has been on the rise, and at present, about 70% of patients need radiation therapy during cancer treatment, and about 40% of patients can be radically treated by radiation therapy, which makes the role and position of radiation therapy in cancer treatment increasingly prominent. At present, a relatively accurate radiation therapy exists in the industry, and the damage of the radiation therapy to the healthy tissues of a human body can be reduced as much as possible. The radioactive substance is placed in the particle bracket and the particle bracket is sent to the lesion part in the patient body, so that the treatment is carried out aiming at the lesion tissue in a targeted way, and the radioactive substance is particularly used for treating cavity cancers such as esophagus cancer, biliary tract cancer and the like. Such particle stents are typically spring-like in form that resiliently bear against the walls of the body tissue tract after being delivered to the lesion to resist displacement. The particle scaffold is typically manufactured by heat setting a tube to a desired spring pattern. However, in the related art, the structure of some particle scaffolds determines that the difficulty of shaping during the heat-setting process is high.
Disclosure of Invention
Based on the design, the particle bracket provided by the invention has smaller shaping resistance in the shaping process, and can reduce the shaping difficulty.
A particle scaffold for placement within a tissue tract, comprising:
the support body, support body can elasticity support in the pipe wall of tissue pipeline, the support body is including being used for holding the hollow pipe of radioactive substance, the outer peripheral face of hollow pipe is provided with along the radial sunken recess of hollow pipe.
In one embodiment, the groove extends spirally on the outer circumferential surface of the hollow tube to form a spiral groove.
In one embodiment, the axial direction of the hollow tube is taken as a first axial direction, the head end of the spiral groove is close to one end of the hollow tube along the first axial direction, and the tail end of the spiral groove is close to the other end of the hollow tube along the first axial direction.
In one embodiment, the circumference of the cross section of the hollow tube is L, and after the side surface of the hollow tube is unfolded, the distance between two adjacent sections of the spiral groove along the first axial direction is L 1 ，0.1L＜L 1 ＜0.2L；L 1 /L＝tanα 1 ，5°＜α 1 ＜10°。
In one embodiment, the spiral groove comprises a first area and a second area which are alternately distributed along the first axial direction, and after the side surface of the hollow tube is unfolded, the distance between two adjacent sections in the first area of the spiral groove along the first axial direction is L 4 The distance between two adjacent sections in the second region of the spiral groove along the first axial direction is L 5 ，L 4 ≠L 5 。
In one of themIn one embodiment, after the side of the hollow tube is unfolded, the first region has a dimension L along the first axial direction 2 The second region has a dimension L along the first axial direction 3 The circumference of the cross section of the hollow tube is L, the hollow tube comprises a plurality of abutting areas for abutting against the same side of the tube wall, so that the formed spiral support body is axially in a second axial direction, and the adjacent two abutting areas are L in the first axial direction 6 ；
L 2 +L 3 ＝0.5L 6 ，0.125L 6 ＜L 2 ＜0.25L 6 ，0.25L 6 ＜L 3 ＜0.375L 6 ；
L 4 /L＝tanα 2 ，L 5 /L＝tanα 3 ，5°＜α 2 ＜α 3 ＜10°；
0.1L＜L 4 ＜L 5 ＜0.2L。
In one embodiment, the circumference of the cross section of the hollow tube is L, the plurality of spiral grooves are formed in the outer circumferential surface of the hollow tube, any two adjacent spiral grooves are staggered along the self axial direction of the hollow tube, and any two adjacent spiral grooves are staggered along the self circumferential direction of the hollow tube, so that the plurality of spiral grooves are arranged in the outer circumferential surface of the hollow tube at intervals in a spiral shape.
In one embodiment, the helical groove has a dimension L in its own extension 7 ，
In one embodiment, the outer peripheral surface of the hollow tube is provided with a plurality of groups of spiral groove assemblies, the spiral groove assemblies comprise a plurality of spiral grooves arranged on the outer peripheral surface of the hollow tube, any two adjacent spiral grooves in the spiral groove assemblies are staggered along the axial direction of the hollow tube, and any two adjacent spiral grooves are staggered along the circumferential direction of the hollow tube, so that the plurality of spiral grooves in the spiral groove assemblies are arranged on the outer peripheral surface of the hollow tube at intervals in a spiral shape; two adjacent groups of spiral groove components are staggered along the self circumferential direction of the hollow pipe, and two adjacent groups of spiral groove components are staggered along the self axial direction of the hollow pipe.
In one embodiment, the grooves extend along the circumferential direction of the hollow tube, and the grooves are arranged at intervals along the axial direction of the hollow tube.
In one embodiment, the axial dimension of the central position of the groove is smaller than the axial dimension of the end position of the groove in the extending direction of the groove.
In one embodiment, the groove is positioned on one side of the outer peripheral surface of the hollow tube, which is close to the axis of the particle support, and the distance from any position of the groove to the tissue pipeline opposite to the groove is larger than the radius of the cross section of the hollow tube along the axial direction of the particle support.
In one embodiment, the hollow tube has a cross-sectional perimeter of L, and the groove has a dimension L in the circumferential direction 8 ,
The particle holder includes a holder body including a hollow tube for containing a radioactive substance, and a groove recessed in a radial direction of the hollow tube is provided on an outer peripheral surface of the hollow tube. Through set up the recess at the outer peripheral face of hollow tube, can increase the flexibility of hollow tube, make the hollow tube become the deformation resistance of heliciform support main part in-process less at the heat setting, the design degree of difficulty is lower.
Drawings
FIG. 1 is a schematic view of a particle scaffold in the related art;
FIG. 2 is a schematic side view of a hollow tube prior to heat setting of a particle scaffold according to an embodiment of the present invention;
FIG. 3 is an enlarged view of a portion of FIG. 2 at A;
FIG. 4 is a schematic illustration of the particle scaffold of the embodiment of FIG. 2 disposed within a tissue tract;
FIG. 5 is a schematic side view of a hollow tube prior to heat setting of a particle scaffold according to another embodiment of the present invention;
FIG. 6 is a partial enlarged view at B in FIG. 5;
FIG. 7 is an enlarged view of a portion of FIG. 5 at C;
FIG. 8 is a schematic view of the embodiment of FIG. 5 with a particle scaffold disposed within a tissue tract;
FIG. 9 is a schematic side-view of a hollow tube prior to heat setting of a particle scaffold in accordance with yet another embodiment of the present invention;
FIG. 10 is a partial enlarged view at D in FIG. 9;
FIG. 11 is a schematic illustration of the particle scaffold of the embodiment of FIG. 9 disposed within a tissue tract;
FIG. 12 is a schematic side-view of a hollow tube prior to heat setting of a particle scaffold according to yet another embodiment of the present invention;
FIG. 13 is an enlarged view of a portion of FIG. 12 at E;
FIG. 14 is a schematic view of the embodiment of FIG. 12 with a particle scaffold disposed within a tissue tract;
FIG. 15 is a schematic cross-sectional view showing the structure of a particle scaffold in accordance with yet another embodiment of the present invention;
FIG. 16 is a schematic view of the position of the stent body and inner tube of the particle stent of the embodiment of FIG. 15;
FIG. 17 is a schematic cross-sectional view of a sealing plug of a particle cradle in accordance with yet another embodiment of the invention;
FIG. 18 is a schematic cross-sectional view of the structure of the particle scaffold in the embodiment of FIG. 17;
FIG. 19 is a schematic view showing the structure of an inner tube of a particle scaffold according to still another embodiment of the present invention;
fig. 20 is a schematic cross-sectional view of a middle section of the particle scaffold in the embodiment of fig. 19.
Reference numerals:
a tissue tract 100;
the particle beam 200, the beam body 210, the groove 211, the first region 212, the second region 213, the connection plug 220, the sealing plug 230, the barrier 2301, the auxiliary barrier 2302, the projection 2303, the transition surface 2304, the coating 240, the inner tube 250, the inversion portion 2501, and the projection 2502.
Detailed Description
In order that the above objects, features and advantages of the invention will be readily understood, a more particular description of the invention will be rendered by reference to the appended drawings. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present invention. The present invention may be embodied in many other forms than described herein and similarly modified by those skilled in the art without departing from the spirit of the invention, whereby the invention is not limited to the specific embodiments disclosed below.
In the description of the present invention, it should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential", etc. indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings are merely for convenience in describing the present invention and simplifying the description, and do not indicate or imply that the device or element being referred to must have a specific orientation, be configured and operated in a specific orientation, and therefore should not be construed as limiting the present invention.
Furthermore, the terms "first," "second," and the like, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In the description of the present invention, the meaning of "plurality" means at least two, for example, two, three, etc., unless specifically defined otherwise.
In the present invention, unless explicitly specified and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally formed; can be mechanically or electrically connected; either directly or indirectly, through intermediaries, or both, may be in communication with each other or in interaction with each other, unless expressly defined otherwise. The specific meaning of the above terms in the present invention can be understood by those of ordinary skill in the art according to the specific circumstances.
In the present invention, unless expressly stated or limited otherwise, a first feature "up" or "down" a second feature may be the first and second features in direct contact, or the first and second features in indirect contact via an intervening medium. Moreover, a first feature being "above," "over" and "on" a second feature may be a first feature being directly above or obliquely above the second feature, or simply indicating that the first feature is level higher than the second feature. The first feature being "under", "below" and "beneath" the second feature may be the first feature being directly under or obliquely below the second feature, or simply indicating that the first feature is less level than the second feature.
It will be understood that when an element is referred to as being "fixed" or "disposed" on another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present. The terms "vertical," "horizontal," "upper," "lower," "left," "right," and the like are used herein for illustrative purposes only and are not meant to be the only embodiment.
Referring to fig. 1, in the related art, the particle holder includes a holder body 210, a connection plug 220 and a sealing plug 230, one end of the holder body 210 is connected with the connection plug 220, and the other end is connected with the sealing plug 230. Referring to fig. 4, 8, 11 and 14, the particle scaffold 200 of the present application may be placed within a tissue tract 100, where the tissue tract 100 is the tract where a tumor or lesion is located or the tract closest to the tumor site. The particle scaffold 200 comprises a scaffold body 210, the scaffold body 210 can be elastically abutted against the wall of the tissue pipeline 100, the scaffold body 210 comprises a hollow tube which is spirally wound, the lumen of the hollow tube is used for containing radioactive substances, and the outer circumferential surface of the hollow tube is provided with a groove 211 which is recessed along the radial direction of the hollow tube. Specifically, the hollow tube is deformed by heat setting to form the helical stent body 210. The hollow tube is made of a shape memory alloy, has a certain elasticity after being heat-set into the stent body 210, and can be stably maintained at the lesion site by being pressed against the wall of the tissue tract 100 by its own elastic resilience after being fed into the tissue tract 100. The cavity of the hollow tube carries radioactive substances, so that the pathological change position can be subjected to radioactive treatment. After the treatment is completed, the particle scaffold 200 is recovered by the recovery device and taken out of the body. According to the particle bracket 200, the groove 211 recessed inwards along the radial direction is formed in the outer circumferential surface of the hollow tube, so that the flexibility of the hollow tube can be increased, the deformation resistance of the hollow tube in the bending deformation process is smaller, the shaping is more convenient, and the shaping difficulty is lower.
Referring to fig. 4, 8 and 11, in some embodiments, the grooves 211 extend spirally on the outer circumference of the hollow tube to form spiral grooves. The spiral groove which is recessed inwards along the radial direction of the hollow pipe is formed in the outer peripheral surface of the hollow pipe, so that the flexibility of the hollow pipe can be increased, the deformation resistance of the hollow pipe in the bending deformation process is smaller, the shaping is more convenient, and the shaping difficulty is lower. Meanwhile, since the grooves 211 extend in a spiral shape, and the different areas in the spiral groove are limited by pulling each other in the axial direction of the hollow tube, the supporting strength of the hollow tube on the wall of the tissue pipeline 100 can be increased when the hollow tube is placed in the tissue pipeline 100 after heat setting, so that the particle bracket 200 is not easy to shift after being placed in a preset position in the tissue pipeline 100, and can be stably kept in the preset position for radiation treatment.
For convenience of description and understanding, in the following embodiments, the axial direction of the hollow tube is taken as a first axial direction, and the axial direction of the helical stent body 210 formed by heat setting the hollow tube is taken as a second axial direction, that is, the axis in the first axial direction is a rotation center line extending along the hollow tube, and when the hollow tube is in a straight state, the first axial direction and the second axial direction are in the same direction.
Referring to fig. 4 and 8, in particular, in some embodiments, the leading end of the helical groove is near one end of the hollow tube in the first axial direction, and the trailing end of the helical groove is near the other end of the hollow tube in the first axial direction. Referring to fig. 4 and 8, it can be seen that only a single spiral groove is provided on the hollow tube, and the spiral groove has a relatively large length and can extend from one axial end of the hollow tube to the other axial end. The provision of the single helical groove 211 allows for better support strength in each region of the hollow tube due to the limitation of the mutual pulling between the segments of the helical groove, thereby increasing the flexibility of the hollow tube and simultaneously compromising the support strength after shaping, so that the particle stent 200 is not easy to shift after being placed at a predetermined position in the tissue tract 100, and can be stably maintained at the predetermined position for radiation therapy. And when the groove 211 is cut, only one groove needs to be cut, so that the operation is simpler.
Referring to fig. 2-4, in some embodiments, preferably, the hollow tube has a cross-sectional perimeter of L, and the adjacent sections of the helical groove are spaced apart in the first axial direction by a distance L in the first axial direction after the side surfaces of the hollow tube are deployed 1 ，0.1L＜L 1 ＜0.2L；L 1 /L＝tanα 1 ，5°＜α 1 Less than 10 deg.. Specifically, fig. 2 is a side-expanded view of the hollow tube, and the cross-sectional perimeter L of the hollow tube is the width of a rectangle of the side-expanded view, and the length of the rectangle is the first axial length of the hollow tube. In the unfolded view, the spiral groove comprises a plurality of sections which are distributed at intervals along the first axial direction, and the distance between two adjacent sections along the first axial direction is L 1 From the trigonometric function, L 1 /L＝tanα 1 . Will L 1 The size of (2) is limited within the above range, L can be avoided 1 Oversized resulting in insufficient flexibility while avoiding L 1 The undersize results in insufficient support strength after sizing, thereby compromising its flexibility and support strength after sizing, not only facilitating sizing, but also being less prone to displacement within the tissue tract 100 after sizing. Will be alpha 1 The limitation of the above range can avoid insufficient flexibility caused by overlarge angle, and simultaneously can avoid stretching out the cutting position when the hollow tube is bent into a spiral shape in the shaping processToo large a gap to facilitate sealing of the particle scaffold 200; in addition, the support strength after shaping is not enough due to the fact that the angle is too small can be avoided, so that flexibility and the support strength after shaping are both considered, shaping is convenient, and the support strength after shaping is not easy to shift when the support is placed in the tissue pipeline 100.
Referring to fig. 5-8, in some embodiments, the helical groove preferably includes first regions 212 and second regions 213 alternately disposed along the first axial direction, and after the side of the hollow tube is expanded, adjacent two sections of the first region 212 of the helical groove are spaced apart from each other along the first axial direction by a distance L 4 The distance between two adjacent sections in the first axial direction in the second region 213 of the spiral groove is L 5 ，L 4 ≠L 5 . Specifically, the degree of the density of different regions in the spiral groove along the first axial direction is different, and the pitch of the different regions can be approximately considered to be different. Specifically, in the embodiment shown in the drawings, the spiral grooves are dense areas with a smaller pitch in the first area 212, and the spiral grooves are open areas with a larger pitch in the second area 213. The first area 212 can greatly increase flexibility of the hollow tube, so that deformation resistance of the hollow tube in the bending deformation process is smaller, shaping is more convenient, and shaping difficulty is lower. The second region 213 can greatly increase the supporting strength of the hollow tube, so that the hollow tube is not easy to shift when being placed at a preset position in the tissue tract 100 after being shaped, and can be stably kept at the preset position for radiation therapy. By means of the alternate density and flexibility, flexibility and support strength after shaping can be simultaneously considered, shaping is facilitated, and the support is not easy to shift after shaping and placed in the tissue pipeline 100.
Referring to fig. 5-8, in some embodiments, the first region 212 preferably has a dimension L in the first axial direction after the side of the hollow tube is deployed 2 The second region 213 has a dimension L in the first axial direction 3 The circumference of the cross section of the hollow tube is L, the hollow tube comprises a plurality of abutting areas for abutting against the same side of the tube wall, and the two adjacent abutting areas have the dimension L along the first axial direction in the second axial direction 6 ；L 2 +L 3 ＝0.5L 6 ，0.125L 6 ＜L 2 ＜0.25L 6 ，0.25L 6 ＜L 3 ＜0.375L 6 ；L 4 /L＝tanα 2 ，L 5 /L＝tanα 3 ，5°＜α 2 ＜α 3 ＜10°；0.1L＜L 4 ＜L 5 < 0.2L. Specifically, in the view of fig. 8, the plurality of abutting regions are a plurality of regions on the hollow tube that abut against the upper wall of the tissue tract 100, or a plurality of regions that abut against the lower wall of the tissue tract 100. In the second axial direction, the distance between two adjacent abutting areas along the first axial direction is L 6 L can also be considered as 6 Is the length of one circle of bending rotation when the hollow tube is shaped. Will be alpha 2 And alpha is 3 The limitation of the above range can avoid insufficient flexibility caused by overlarge angle, and simultaneously, the problem that the sealing of the particle bracket 200 is not facilitated because an overlarge gap is stretched at a cutting part when the hollow tube is bent to be in a spiral shape in the shaping process can be avoided; meanwhile, the defect that the support strength is insufficient after shaping due to the fact that the angle is too small can be avoided, so that the flexibility and the support strength after shaping are both considered, shaping is convenient, and the support strength is not easy to shift after shaping and is placed in the tissue pipeline 100. Will L 2 And L is equal to 3 The flexible and supporting strength can be balanced well within the range, and L is avoided 3 Too large (i.e., the second region 213 is too large in ratio) resulting in insufficient flexibility, avoiding L 3 Too small (i.e., the second region 213 is too small in ratio) to result in insufficient support strength after sizing; while avoiding L 2 Too large (i.e., the first region 212 is too large in ratio) results in insufficient support strength after sizing, avoiding L 2 Too small (i.e., the first region 212 is too small in duty cycle) results in insufficient flexibility, thereby compromising its flexibility and post-sizing support strength, not only facilitating sizing, but also being less prone to displacement within the tissue tract 100 after sizing. Will L 4 And L is equal to 5 Within the above range, L can be avoided 4 And L is equal to 5 Oversized resulting in insufficient flexibility while avoiding L 4 And L is equal to 5 The undersize results in insufficient support strength after sizing, thereby compromising its flexibility and support strength after sizing, not only facilitating sizing, but also being less prone to displacement within the tissue tract 100 after sizing.
Referring to fig. 9 to 11, in some embodiments, the cross-sectional circumference of the hollow tube is L, a plurality of spiral grooves are disposed on the outer circumferential surface of the hollow tube, any two adjacent spiral grooves are staggered along the self axial direction of the hollow tube, and any two adjacent spiral grooves are staggered along the self circumferential direction of the hollow tube, so that the plurality of spiral grooves are arranged on the outer circumferential surface of the hollow tube at intervals in a spiral shape. Specifically, each groove 211 is in a spiral shape, and the plurality of grooves 211 are arranged in a spiral shape. Because each groove 211 is spiral, the flexibility of the hollow tube can be increased, so that the hollow tube is easy to bend and deform, and because the grooves 211 are mutually independent, the supporting strength of the hollow tube can be improved by the solid tube wall between the adjacent grooves 211, and the hollow tube has both flexibility and supporting strength.
Preferably, in some embodiments, the helical groove has a dimension L in its own direction of extension 7 ，2/3L＜L 7 < 3/4L. Will L 7 The size of the steel is limited in the range, so that the steel can be prevented from being oversized to cause insufficient strength, and the risk of breakage in the bending deformation process is reduced; at the same time, the bending deformation difficulty caused by insufficient flexibility due to undersize is avoided. Preferably, the adjacent groove walls of each groove 211 are smoothly transited by fillets to relieve stress concentration during bending deformation, so that the hollow tube is not easily broken. In addition, the width w1 of the grooves 211, the distance d1 between adjacent grooves 211 along the arrangement direction, and the angle α between the length direction of the grooves 211 and the width direction of the side development view can be adjusted according to practical requirements 4 Thereby obtaining proper flexibility and support strength.
Preferably, in some embodiments, the outer peripheral surface of the hollow tube is provided with a plurality of groups of spiral groove assemblies, the spiral groove assemblies comprise a plurality of spiral grooves arranged on the outer peripheral surface of the hollow tube, any two adjacent spiral grooves in the spiral groove assemblies are staggered along the self axial direction of the hollow tube, and any two adjacent spiral grooves are staggered along the self circumferential direction of the hollow tube, so that the plurality of spiral grooves in the spiral groove assemblies are arranged on the outer peripheral surface of the hollow tube at intervals in a spiral shape; the adjacent two groups of spiral groove components are staggered along the self circumference of the hollow pipe, and the adjacent two groups of spiral groove components are staggered along the self circumference of the hollow pipe. Specifically, the plurality of grooves 211 in a spiral arrangement mentioned in the previous embodiment may be regarded as a set of spiral groove assemblies, and in some embodiments, a set of spiral groove assemblies is added in the manner of the previous embodiment, and the two sets of spiral groove assemblies are staggered from the self circumference of the hollow tube along the first axial direction. By arranging two groups of spiral groove components, the flexibility of the hollow tube can be further increased, so that the hollow tube is easier to bend and deform. In other embodiments, the number of helical groove assemblies may be more than two.
Referring to fig. 12 to 14, in some embodiments, the grooves 211 extend in the circumferential direction of the hollow tube, and the plurality of grooves 211 are spaced apart in the axial direction of the hollow tube. The grooves 211 extend along the circumferential direction of the hollow tube, so that the flexibility of the hollow tube can be greatly improved, and the hollow tube is easy to bend and deform. Meanwhile, as the grooves 211 are mutually independent, the solid pipe wall between the adjacent grooves 211 can improve the supporting strength of the hollow pipe, thereby having flexibility and supporting strength. Preferably, the region where the grooves 211 are located is mostly located inside the particle scaffold 200, i.e. on the side not in contact with the tissue tract 100, when it is bent, the flexibility is increased by the grooves 211, accommodating a larger degree of deformation inside. At the same time, the outside of the particle scaffold 200 can be made as smooth as possible, friction with the tissue tract 100 can be reduced, and risk of damaging the tissue tract 100 can be reduced.
Preferably, in some embodiments, the axial dimension of the central position of the groove 211 is smaller than the axial dimension of the end positions of the groove 211 along the extending direction of the groove 211. Specifically, the width of the groove 211 at the center is small, and the width at the both ends is large. In the bending deformation process of the hollow tube, the positions of the two ends of the groove 211 are twisted to a larger extent, and the larger size of the groove can better provide a torsional deformation space, so that the hollow tube can be smoothly bent and deformed. Preferably, the adjacent groove walls of each groove 211 are smoothly transited by fillets to relieve stress concentration during bending deformation, so that the hollow tube is not easily broken.
Preferably, in some embodiments, since the particle scaffold 200 is a hollow tube for placing radioactive material into the tissue tract 100, the radioactive material is injected or placed into the particle scaffold 200, and for the wall of the particle scaffold 200, it is provided with a portion of insulating material and a portion of penetrating material, further, since the groove 211 will thin the wall thickness of the position where it is located, the groove 211 is used as a penetrating portion of the radioactive material, and still further, the groove 211 is provided on the side of the outer peripheral surface of the particle scaffold 200 near the axis (i.e. the second axis) thereof, i.e. the inner side of the whole particle scaffold 200, so as to avoid the groove 211 from being blocked into the tissue tract 100 or getting too close to the tissue tract 100. Since the particle scaffold 200 extends along a helical structure, the distance from any point on the groove 211 to the tissue tract 100 it is facing is always greater than the radius of the particle scaffold 200, thereby avoiding excessive irradiation of the tissue tract by radioactive materials.
Preferably, in some embodiments, the hollow tube has a cross-sectional perimeter L and the groove 211 has a circumferential dimension L 8 ,2/3L＜L 8 < 3/4L. Will L 8 The size of the steel is limited in the range, so that the steel can be prevented from being oversized to cause insufficient strength, and the risk of breakage in the bending deformation process is reduced; at the same time, the bending deformation difficulty caused by insufficient flexibility due to undersize is avoided. In addition, the width w2 of the end portion of the groove 211, the width w3 of the center portion, and the distance d2 between adjacent grooves 211 along the first axial direction can be adjusted according to practical requirements during design, so as to obtain proper flexibility and supporting strength.
As described above, since the particle scaffold 200 has the radioactive material carried in the lumen, the radioactive material can be used to treat the lesion, and after the treatment is completed, the particle scaffold 200 is recovered and taken out from the body by the recovery device, and therefore the particle scaffold 200 must ensure the sealing property of the lumen, however, the hollow tube is not sealed in a state where the plurality of grooves in the hollow tube above is penetrated or in a state where the hollow tube is excessively bent, and therefore the surface of the particle scaffold 200 needs to be sealed, specifically referring to the following embodiments:
referring to fig. 15 to 16, specifically, in some embodiments, the particle stand 200 includes a stand body 210, a cover film 240 is provided on the surface of the stand body 210, the cover film 240 is a polymer film, and the material is PTFE or PET, and is generally covered on the surface of the stand 210 by adopting a hot melting or bonding mode, however, because the hot melting and bonding cannot stably cover all grooves, the simple cover film 240 cannot reach the sealing standard of the particle stand 200, and therefore, an inner tube 250 is attached to the inner side of the stand body 210, the inner tube 250 is used as a containing cavity to carry the medicine, and the inner tube 250 has elasticity, and in the middle section of the stand body 210, the inner tube 250 is attached to the inner wall of the stand body 210 and extends along with the stand body 210 until reaching the position of the sealing plug 230, it should be noted that the principle of sealing the connecting plug 220 is consistent except that the connecting structure is different from the sealing plug 230. In the present embodiment, the inner tube 250 covers the end of the stent body 210, specifically, a portion of the inner tube 250 protrudes from the inside of the stent body 210 and is turned over at the end of the stent body 210 to form a turned-over portion 2501, and after this arrangement, the turned-over portion 2501 covers a portion of the outside of the stent body 210, the end of the stent body 210 is completely covered with the inner tube 250 and the cover film 240, and in combination with the arrangement of the sealing plug 230, the drug in the inner tube 250 is not directly oozed out from the boundary of the stent body 210.
The sealing plug 230 includes a baffle 2301 facing the stent body 210, the baffle 2301 surrounding an opening formed facing the stent body 210 to seal the end of the cover 240, the stent body 210, and the inner tube 250, it should be noted that the sealing plug 230 is detachable to ensure that the drug can be injected or placed into the interior of the stent body 210.
Referring to fig. 17-18, preferably, the flap 2301 of the sealing plug 230 protrudes inwardly at its ends to form an auxiliary flap 2302, and the middle portion of the sealing plug 230 protrudes toward the holder body 210 to form a protrusion 2303, the protrusion 2303 being caught inside the inner tube 250. Such a structural arrangement can further improve sealability, in particular, when loading is completed, since a part of the inner tube 250 (i.e., the turning portion 2501) protrudes out of the holder main body when loading of the sealing plug 230 is required, the turning portion 2501 is located outside of the protruding portion 2303, the protruding portion 2303 gradually snaps into the inside of the inner tube 250 as the sealing plug 230 gradually approaches the holder main body 210, the turning portion 2501 approaches toward the bottom of the protruding portion 2303 against the protruding portion 2501, and when reaching the bottom of the protruding portion 2303, the turning portion 2501 naturally turns toward the outside as the loading of the sealing plug 230 due to the inner side of the turning portion 2501 abutting against the protruding portion 2303 without shielding, thereby achieving automatic turning of the turning portion 2501, and the auxiliary baffle 2302 serves to abut and seal the end of the turning portion 2501 to ensure complete sealing of the inner tube 250. It should be noted that if the auxiliary flap 2302 is not present, sealing and automatic inversion can still be achieved by virtue of the projection 2303 and flap 2301, as long as the flap 2301 can ultimately abut the inversion 2501.
Preferably, the pitch of the flap 2301 and the holder body 210 is slightly less than or equal to the thickness of the inversion portion 2501.
Preferably, the auxiliary barrier 2302 is positioned between the end of the holder body 210 and the recess 211 closest to the end when the sealing plug 230 is assembled.
Preferably, the bottom transition surface 2304 of the projection 2303 is an arcuate transition surface or ramp that ensures that the flip 2501 moves in a gradually outward flip direction until the final flip is achieved.
Preferably, the inner tube 250 is made of self-solidifying medical liquid silicone, and the mold rod is inserted through the inner cavity of the bracket body 210, and then the liquid silicone is injected into and fills the gap between the bracket body 210 and the mold rod.
Referring to fig. 17 to 18, preferably, the middle surface of the inner tube 250 is provided with a plurality of protrusions 2502 corresponding to the grooves 211, the protrusions 2502 are corresponding to the grooves 211 of the bracket body 210, and finally are snapped into the grooves 211 of the bracket body 210, so as to achieve the relative fixation of the inner tube 250 and the bracket body 210.
Preferably, the turnover portion 2501 may also be provided with a partial protrusion to be caught inside the groove 211 to form a better sealing effect.
The technical features of the above-described embodiments may be arbitrarily combined, and all possible combinations of the technical features in the above-described embodiments are not described for brevity of description, however, as long as there is no contradiction between the combinations of the technical features, they should be considered as the scope of the description.
The above examples illustrate only a few embodiments of the invention, which are described in detail and are not to be construed as limiting the scope of the invention. It should be noted that it will be apparent to those skilled in the art that several variations and modifications can be made without departing from the spirit of the invention, which are all within the scope of the invention. Accordingly, the scope of protection of the present invention is to be determined by the appended claims.
Claims (13)
1. A particle scaffold, comprising:
the support body, support body can elastically support in the pipe wall of tissue pipeline, the support body is including being used for holding the hollow pipe of radioactive substance, the outer peripheral face of hollow pipe is provided with along the radial sunken recess of hollow pipe.
2. The particle scaffold of claim 1, wherein the grooves extend helically on the outer circumference of the hollow tube to form helical grooves.
3. The particle scaffold of claim 2, wherein the axial direction of the hollow tube is a first axial direction, the head end of the spiral groove is near one end of the hollow tube in the first axial direction, and the tail end of the spiral groove is near the other end of the hollow tube in the first axial direction.
4. A particle scaffold according to claim 3, wherein the hollow tube has a cross-sectional perimeter of L, and the adjacent two segments of the helical groove have a spacing of L along the first axial direction after the side of the hollow tube is deployed 1 ，0.1L＜L 1 ＜0.2L；L 1 /L＝tanα 1 ，5°＜α 1 ＜10°。
5. A particle scaffold according to claim 3, wherein the helical grooves comprise first and second regions alternately distributed along the first axial direction, adjacent ones of the first regions of the helical grooves being disposed in the first axial direction after the side surfaces of the hollow tube are expandedThe distance between the segments along the first axial direction is L 4 The distance between two adjacent sections in the second region of the spiral groove along the first axial direction is L 5 ，L 4 ≠L 5 。
6. The particle scaffold of claim 5, wherein the first region has a dimension L in the first axial direction after the side of the hollow tube is deployed 2 The second region has a dimension L along the first axial direction 3 The circumference of the cross section of the hollow tube is L, the hollow tube comprises a plurality of abutting areas for abutting against the same side of the tube wall, so that the formed spiral support body is axially in a second axial direction, and the adjacent two abutting areas are L in the first axial direction 6 ；
L 2 +L 3 ＝0.5L 6 ，0.125L 6 ＜L 2 ＜0.25L 6 ，0.25L 6 ＜L 3 ＜0.375L 6 ；
L 4 /L＝tanα 2 ，L 5 /L＝tanα 3 ，5°＜α 2 ＜α 3 ＜10°；
0.1L＜L 4 ＜L 5 ＜0.2L。
7. The particle scaffold according to claim 2, wherein the hollow tube has a cross-sectional circumference of L, a plurality of the spiral grooves are provided on an outer circumferential surface of the hollow tube, any adjacent two of the spiral grooves are offset in a self-axial direction of the hollow tube, and any adjacent two of the spiral grooves are offset in a self-circumferential direction of the hollow tube such that the plurality of spiral grooves are arranged on the outer circumferential surface of the hollow tube at a spiral interval.
8. The particle scaffold according to claim 7, wherein the helical groove has a dimension L in its own extension direction 7 ，
9. The particle scaffold according to claim 2, wherein the outer circumferential surface of the hollow tube is provided with a plurality of sets of spiral groove assemblies, the spiral groove assemblies comprise a plurality of spiral grooves arranged on the outer circumferential surface of the hollow tube, any adjacent two of the spiral grooves in the spiral groove assemblies are staggered along the self axial direction of the hollow tube, and any adjacent two of the spiral grooves are staggered along the self circumferential direction of the hollow tube, so that the plurality of spiral grooves in the spiral groove assemblies are arranged on the outer circumferential surface of the hollow tube at intervals in a spiral shape; two adjacent groups of spiral groove components are staggered along the self circumferential direction of the hollow pipe, and two adjacent groups of spiral groove components are staggered along the self axial direction of the hollow pipe.
10. The particle scaffold of claim 1, wherein the grooves extend in a circumferential direction of the hollow tube, and a plurality of the grooves are arranged at intervals in an axial direction of the hollow tube.
11. The particle scaffold of claim 10, wherein the axial dimension of the central location of the groove is smaller than the axial dimension of the end locations of the groove along the direction of extension of the groove.
12. The particle scaffold of claim 10, wherein the groove is located on a side of the outer circumferential surface of the hollow tube near the axis of the particle scaffold, and a distance from any position of the groove to the tissue tract to which it is directly opposite is greater than a radius of a cross section of the hollow tube in the axial direction of the particle scaffold.
13. The particle scaffold of claim 10, wherein the hollow tube has a cross-sectional perimeter L and the groove has a dimension L in the circumferential direction 8 ,
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202111673762.4A CN116407747A (en) | 2021-12-31 | 2021-12-31 | Particle support |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202111673762.4A CN116407747A (en) | 2021-12-31 | 2021-12-31 | Particle support |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN116407747A true CN116407747A (en) | 2023-07-11 |
Family
ID=87056885
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202111673762.4A Pending CN116407747A (en) | 2021-12-31 | 2021-12-31 | Particle support |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN116407747A (en) |
-
2021
- 2021-12-31 CN CN202111673762.4A patent/CN116407747A/en active Pending
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