CN211460698U - Delivery guide wire and treatment device - Google Patents
Delivery guide wire and treatment device Download PDFInfo
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- CN211460698U CN211460698U CN201922079500.XU CN201922079500U CN211460698U CN 211460698 U CN211460698 U CN 211460698U CN 201922079500 U CN201922079500 U CN 201922079500U CN 211460698 U CN211460698 U CN 211460698U
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Abstract
The utility model relates to a carry seal wire and include this treatment device that carries seal wire, carry seal wire includes dabber and membrane structure, the dabber has the loading section, follows the axial of dabber, it forms to encircle to load the section the protruding portion of the axis of dabber forms the depressed part between the adjacent protruding portion, membrane structure sets up at least on the depressed part. Through form concave-convex structure on loading the section for the membrane structure is difficult to take place to shift, and then avoids the phenomenon that the membrane structure takes off the year at the in-process of transfer gantry, improves the reliability and the security of carrying the seal wire.
Description
Technical Field
The utility model relates to the technical field of medical equipment, concretely relates to carry seal wire and treatment device.
Background
Intracranial aneurysms are usually abnormal bulges on the wall of an intracranial artery, and are the first causes of subarachnoid hemorrhage. In cerebrovascular diseases, the incidence of intracranial aneurysm is second to cerebral thrombosis and hypertensive cerebral hemorrhage, and the intracranial aneurysm has great harm.
In the prior art, there are three main methods for treating intracranial aneurysms: (1) the surgical clamping method adopts a metal clamp to clamp the neck of the aneurysm to block intracranial aneurysm and cerebral circulation blood flow, and prevents the rupture and bleeding of the aneurysm while recovering normal blood supply of the parent artery. (2) The intratumoral embolization method adopts embolization materials to fill the aneurysm, so that thrombus is formed in the body of the aneurysm, and the rupture hemorrhage caused by further expansion of the body of the aneurysm is avoided. (3) The intravascular stent method is to implant a stent into a blood vessel to interfere the blood flow entering an aneurysm from a parent artery, so that the blood in the aneurysm is blocked and deposited, thereby forming aneurysm thrombus and further promoting the closure of the aneurysm body to prevent the rupture of the aneurysm body. Since aneurysms typically grow around the cerebral arterial loop, there are many important blood vessels, nerves, and brain tissue around the cerebral arterial loop. When the surgical clamping method is used for treating the aneurysm, the medical requirements of doctors are extremely high, and the death rate of patients who treat the aneurysm by the surgical clamping method is still as high as 50 percent. When the intratumoral embolization method is simply used for treating large or huge complicated aneurysms, the recurrence rate of patients is high. Currently, the most widely used treatment for intracranial aneurysms is endovascular stenting.
When intracranial aneurysm is treated by using an intravascular stent method, the stent is delivered into a blood vessel through a delivery guide wire. The delivery guide wire comprises a mandrel and a membrane structure arranged on the mandrel, the stent is loaded on the membrane structure, and under the action of friction force between the membrane structure and the stent, the stent moves synchronously along with the delivery guide wire. In the prior art, two ends of the film structure are fixed on the mandrel through metal elements, or the film structure is directly adhered to the mandrel. However, because of the thinness and tortuosity of intracranial vessels, the delivery guidewire is small in diameter (the stent-loaded portion of the delivery guidewire is typically between 0.07mm and 0.20mm in diameter), and the delivery guidewire also needs to be flexible. And the flexibility of the conveying guide wire can be reduced by connecting the mandrel with the membrane structure through the metal element, and when the membrane structure and the mandrel are connected by adopting a pasting method, the problem of poor bonding strength of the membrane structure and the mandrel exists due to small contact area, so that in the process of conveying the support, the membrane structure is easy to loosen, fold or shift, and further the condition of support unloading is caused.
SUMMERY OF THE UTILITY MODEL
An object of the utility model is to provide a carry seal wire and medical device, this carry seal wire has good compliance, and can effectively avoid because of the not hard up or aversion support off-loading phenomenon that causes of membrane structure at the in-process of transfer gantry.
To achieve the above object, the present invention provides a pushwire comprising a mandrel and a membrane structure, wherein the mandrel has a loading section, along an axial direction of the mandrel, the loading section is formed with a plurality of protrusions surrounding the mandrel, adjacent to each other, a recess is formed between the protrusions, and the membrane structure is at least partially disposed on the recess.
Optionally, the loading section has a twisted structure formed by twisting, so that the loading section has the protrusion part and the recess part in a continuous spiral shape.
Optionally, a plurality of the protrusions are arranged at intervals or adjacently along the axial direction of the mandrel, and each protrusion extends around the circumference of the mandrel.
Optionally, the membrane structure fills the recess and covers the entire loading section.
Optionally, the number of the film structures is multiple, and the multiple film structures are arranged in the concave part; and/or the film structure is arranged on the side of the projection at the edge facing away from the recess.
Optionally, the distance between two adjacent protrusions is 0.5mm-6 mm.
Optionally, the distance between two adjacent protrusions is 0.5mm-4 mm.
Optionally, the mandrel has opposite proximal and distal ends, and the outer diameter of the plurality of projections decreases sequentially in a direction from the proximal end to the distal end.
Optionally, a transition portion is further disposed between the mandrel and the film structure, the transition portion is hooped on the loading section, and the transition portion has a void structure.
Optionally, the transition portion is welded to the mandrel, or the transition portion is bonded to the mandrel.
Optionally, the transition portion includes a plurality of coils, the plurality of coils are arranged along the axial direction of the mandrel, and the gap structure is formed between two adjacent coils.
Optionally, the transition portion is a helical structure formed by spirally winding a wire along the axis of the mandrel, and the gap structure is formed between the wires of two adjacent turns.
Optionally, the transition portion is a tube mesh structure woven by silk threads, and holes of the tube mesh structure form the void structure.
Optionally, the transition portion is made of a metallic material, the metallic material having developability.
Optionally, the material of the membrane structure includes any one or more of thermoplastic elastomer, thermoplastic polyurethane elastomer, silicone, nylon and acrylic polymer.
To achieve the above object, the present invention further provides a therapeutic device, comprising a delivery tube, a medical implant and the delivery guide wire, wherein the delivery tube has an inner cavity running through in the axial direction, the inner cavity is used for accommodating the medical implant, and the wall of the inner cavity presses the medical implant to compress the medical implant; the compressed medical implant is sleeved on the membrane structure.
Optionally, the medical implant is a self-expanding stent.
Optionally, the lumen has a radial dimension in a range of 0.017 inches to 0.029 inches.
Compared with the prior art, the utility model discloses a carry seal wire and treatment device has following advantage:
the delivery guide wire comprises a mandrel and a film structure, wherein the mandrel is provided with a loading section, the loading section is provided with protruding parts along the axial direction of the mandrel, concave parts are formed between the adjacent protruding parts, and the film structure is at least partially arranged in the concave parts. And applying the delivery guide wire to a treatment device, wherein the treatment device further comprises a delivery pipe and a medical implant, the delivery pipe is used for accommodating and compressing the medical implant, and the compressed medical implant is sleeved on the membrane structure. By disposing the membrane structure in the recess, the protrusion can act as a stopper to restrain the membrane structure, so that the membrane structure is difficult to displace, thereby reducing the possibility of unloading the stent.
Work as the membrane structure fills the depressed part to the cladding is whole when loading on the section, the existence of protruding portion has still increased the membrane structure with bonding area between the dabber has improved the cohesion between membrane structure and the dabber, not only makes the membrane structure be difficult to shift, still makes the membrane structure be difficult to the fold that appears, further reduces the possibility that the support unloaded, improves the reliability and the security of carrying the seal wire.
Drawings
FIG. 1 is a schematic view of a prior art treatment apparatus;
fig. 2a is a schematic structural view of a pushwire according to a first embodiment of the present invention, in which a membrane structure is not shown;
FIG. 2b is a schematic view of a pushwire according to a first embodiment of the present invention, showing a membrane structure disposed only in the depression;
fig. 2c is a schematic view of a delivery guidewire according to a first embodiment of the present invention, showing a membrane structure wrapped around the entire loading segment;
fig. 3a is a schematic diagram of a delivery guidewire according to a second embodiment of the present invention, wherein the membrane structure is not shown;
FIG. 3b is a schematic view of a pushwire according to a second embodiment of the present invention, showing a membrane structure disposed only in the depression;
FIG. 3c is a schematic representation of a pushwire according to a second embodiment of the present invention, showing a membrane structure covering the entire loading segment;
fig. 4a is a schematic structural view of a pushwire according to a third embodiment of the present invention, in which a membrane structure is not shown;
fig. 4b is a schematic structural view of a pushwire according to a third embodiment of the present invention, showing a membrane structure covering the entire loading segment.
In the figure:
10, 100-delivery guide wire;
11, 110-mandrel, 111-projection, 112-depression;
L1-a loading section;
12, 120-membrane structure;
130-a first development;
140-a second development;
150-a reducing spring;
20-a scaffold;
30-conveying pipe.
Detailed Description
To make the objects, advantages and features of the present invention clearer, the present invention will be described in further detail with reference to the accompanying drawings. It should be noted that the drawings are in simplified form and are not to precise scale, and are provided for convenience and clarity in order to facilitate the description of the embodiments of the present invention.
As used in this specification, the singular forms "a", "an" and "the" include plural referents, and the plural forms "a plurality" includes more than two referents unless the content clearly dictates otherwise. As used in this specification, the term "or" is generally employed in its sense including "and/or" unless the content clearly dictates otherwise, and the terms "mounted," "connected," and "connected" are to be construed broadly, e.g., as meaning either fixedly connected, detachably connected, or integrally connected. Either mechanically or electrically. Either directly or indirectly through intervening media, either internally or in any other relationship. 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 same or similar reference numbers in the drawings identify the same or similar elements.
As used herein, the terms "proximal" and "distal" refer to the relative orientation, relative position, and orientation of elements or actions with respect to one another from the perspective of an operator using the medical device, although "proximal" and "distal" are not intended to be limiting, but generally refers to the end of the medical device that is closer to the operator during normal operation, and generally refers to the end that is first introduced into the patient.
Fig. 1 shows a schematic structural view of a prior art treatment apparatus for delivering a medical implant, such as a stent, to a predetermined location in a patient. As shown in fig. 1, the therapeutic device includes a delivery guide wire 10, a stent 20 and a delivery tube 30, the delivery guide wire 10 includes a core shaft 11 and a membrane structure 12 disposed on the core shaft 11, the delivery tube 30 has an inner cavity running through axially, the inner cavity is used for accommodating the stent 20, and the wall of the inner cavity presses the stent 20, so that the stent 20 is compressed, and the compressed stent 20 is sleeved on the membrane structure 12. In order to smoothly push the delivery wire in the delivery tube 30, the conventional delivery wire 10 is made of a metal material and has a smooth outer surface, and the membrane structure 12 is disposed on the core shaft 11 of the delivery wire 10 to increase the first friction between the delivery wire 10 and the stent 30, and generally, the membrane structure 12 is made of a polymer material with a relatively high friction coefficient and is connected to the core shaft 11 made of a metal material by an adhesion method.
In the treatment device, the duct 30, the stent 20, and the delivery guidewire 10 are in an interference state, that is, the duct 10 applies a radial force to the stent 20, and the stent 20 applies a force to the delivery guidewire 10 (specifically, the membrane structure 12). When the operator pushes the pushwire 10 to axially move the pushwire 10 in the delivery tube 30, a first friction force is generated between the pushwire 10 and the inner surface of the stent 20, and the stent 20 can move synchronously with the pushwire 10 under the action of the friction force. At the same time, a second friction force is generated between the outer surface of the stent 20 and the inner wall of the delivery tube 30, and when the second friction force is too large, the membrane structure 12 will be loosened, wrinkled or even displaced, and the stent 20 will be unloaded.
In view of this, the present invention provides a conveying guide wire for conveying a medical implant to a predetermined position in a patient, which can effectively reduce the probability of occurrence of unloading the medical implant, and improve the safety and reliability of the conveying guide wire. The medical implant is, for example, a self-expanding stent (i.e., a self-expanding stent), which may be, in particular, a braided stent or a cut stent. In other embodiments, the medical implant may also be a medical embolic coil, a vascular occlusion device, or the like, without limitation. Hereinafter, for the convenience of description, the medical implant is described as a self-expandable stent, and for the sake of simplicity, the self-expandable stent is uniformly referred to as a "stent".
As shown in FIGS. 2a and 2b, a pushwire 100 according to a first embodiment of the present invention includes a mandrel 110 and a membrane structure 120, the mandrel 110 having a loading section L1The loading section L is arranged along the axial direction of the mandrel 1101Having protrusions 111 formed around the mandrel 110, and recesses 112 formed between adjacent protrusions 111, the film structure 120 being at least partially disposed at the recesses 112.
In particular, the loading section L1Has a plurality of protrusions 111 thereon, and each of the protrusions 111 extends around the circumference of the mandrel 110. Each of the protrusions 111 may be a continuous annular protrusion, or each of the protrusions 111 may include a plurality of sub-protrusions arranged at intervals in the circumferential direction of the mandrel 110. The extending direction of each protrusion 111 may be perpendicular to the axis of the mandrel 110 (i.e., the plane of the protrusion 111 is perpendicular to the axis of the mandrel 110), or may be non-perpendicular to the axis (i.e., the plane of the protrusion 111 is not perpendicular to the axis of the mandrel 110).
In this embodiment, the mandrel 110 is made of a metal (including an alloy) material. By grinding the mandrel 110, the loading section L can be formed1A plurality of the protruding portions 111 are formed, and two adjacent protruding portions 111 are disposed in close proximity in the present embodiment. The outer contour of the axial cross section of the protruding portion 111 is an arc structure, so that a V-shaped recess 112 is formed between two adjacent protruding portions 111. It is understood that the recess 112 of the present embodiment is relative to the protrusion 111, as long as the outer diameter of the recess 112 is smaller than the outer diameter of the protrusion 111 located at both sides of the recess 112, and the recess is also referred to hereinafter.
Said loading section L being normally1There are provided n projections 111, n may be two, three, four or more. Alternatively, as shown in fig. 2b, the membrane structure 120 is only arranged at the recess 112, in other words, the loading section L1N-1 membrane structures 120 may be arranged at intervals (when the membrane structures 120 are arranged on the sides of the two outermost protrusions 111 facing away from the recess 112, the number of the membrane structures 120 is n +1, and of course, the number of the membrane structures 120 may also be n), and the number of the protrusions 111 is specifically designed according to the length of the stent to be delivered, so as to determine the number of the membrane structures 120. In this case, the membrane structure 120 can be displaced only after the membrane structure is folded over the protrusion 111, that is, the protrusion 111 acts as a limiting structure to block the displacement of the membrane structure 120, which increases the difficulty of displacing the membrane structure 120.
Alternatively, as shown in fig. 2c, the membrane structure 120 may cover the entire loading section L1I.e. the film structure 120 fills the recess 112 and covers the protrusion 111, the film structure 120 may further extend to the side of the protrusion 111 facing away from the recess 112. In this way, the protrusion 111 not only can serve as a limit, but also the membrane structure 120 and the loading section L1Has a larger bonding area, thereby improving the bonding force between the film structure 120 and the mandrel 110The difficulty of shifting the membrane structure 120 is increased, the problems of folds and looseness of the membrane structure 120 can be effectively solved, and the safety and reliability of the whole conveying guide wire 100 are further improved.
For this version of the pushwire 100, the membrane structure 120 may be dip coated and placed on the mandrel 110 by die-casting, or may be placed in other ways, such as first in the loading section L1Sleeving a polymer tube, sleeving a heat shrink tube outside the polymer tube, heating the heat shrink tube, shaping by using a mold to melt the polymer tube and infiltrate the polymer tube into the concave part 111, and removing the heat shrink tube after the polymer material is cooled and solidified. In addition, an adhesive may be added between the mandrel 110 and the polymer tube to enhance the connection strength between the mandrel and the polymer tube. In this embodiment, the material of the film structure 120 may be selected from any one or more of thermoplastic elastomers such as block polyether amide (Pebax) or Thermoplastic Polyurethane (TPU) elastomer, silicone, nylon, acrylic polymer, and other polymer materials.
Further, the pushwire 100 further comprises a transition portion (not shown) disposed between the membrane structure 120 and the mandrel 110. The transition part is fixedly arranged on the loading section L1And the transition portion has a void structure, such that the membrane structure 120 fills the void structure and covers the outer surface of the transition portion. The transition part is fixedly arranged on the loading section L1And the film structure 120 has a larger contact area with the transition portion, thereby indirectly enhancing the bonding force between the film structure 120 and the mandrel 110. Preferably, the transition portion may be welded or bonded to the loading section L1And (4) connecting.
The transition portion may be made of wire and the configuration of the transition portion may have a variety of options. For example, the transition portion may include a plurality of coils, and the plurality of coils may be spaced along the axial direction of the mandrel 110 such that the void structure is formed between adjacent coils. For another example, the transition portion is a spiral structure formed by spirally winding a metal wire along the axis of the mandrel 110, and two adjacent turns of the metal wire may be separated from each other to form the void structure. For another example, the transition portion is a tube mesh structure woven by metal wires, and the holes of the tube mesh structure form the void structure. In summary, the transition may indirectly enhance the bonding force between the film structure 120 and the mandrel 110.
The transition part is preferably made of a metal material with developability, and the metal material with developability includes, but is not limited to, one or more of platinum, gold, tungsten, platinum alloy, platinum-tungsten alloy, platinum-iridium alloy and platinum-nickel alloy, for example, the transition part may be made of platinum-tungsten alloy alone, platinum-iridium alloy alone, or both platinum-tungsten alloy and platinum-iridium alloy (for example, the transition part of the pipe-mesh structure is woven by platinum-tungsten alloy wires and platinum-iridium alloy wires together). The purpose of this is that the operator can easily observe the position of the membrane structure 120 when delivering the stent and judge whether the stent can be recovered. In particular, when the pushwire is used to deliver a stent, the stent is sleeved over the pushwire and compressed within a delivery tube having opposite first proximal and distal ends with a visualization ring disposed at the first distal end. When the support is in by the suit after the conveyer pipe compression on the membrane structure, and along with after the conveying seal wire gets into the human body, the operator can see in real time from developing device the position of membrane structure 120, in case membrane structure 120 begin with the coincidence appears in the development ring, can judge when resuming to distal end propelling movement support, the support just can not retrieve again, has reduced the operation degree of difficulty.
With continued reference to fig. 2 a-2 c, optionally, the delivery guidewire 100 further includes a first developing member 130 and a second developing member 140, the mandrel 110 has a second proximal end and a second distal end opposite to each other, the first developing member 130 is disposed at the end of the second distal end, the second developing member 140 is disposed on the mandrel 110, and the loading section L is disposed on the loading section L1Between the first developing member 130 and the second developing member 140. In thatWhen the stent is delivered, the operator can judge the position of the delivery guide wire 100 according to the first developing part 130 and the second developing part 140.
Optionally, the mandrel 110 comprises at least one variable diameter section and at least one constant diameter section, the constant diameter section and the variable diameter section are alternately arranged from the second proximal end to the second distal end, and the diameter of any one of the variable diameter sections is gradually reduced. And for the same variable diameter section, the variable diameter section is provided with a third proximal end and a third distal end which are opposite, and the diameter of the constant diameter section connected with the third proximal end is larger than that of the constant diameter section connected with the third distal end. Through the arrangement of the reducing section, the structure of the whole conveying guide wire 100 is approximately conical, so that the flexibility, the conveying force conductivity and the tracking performance of the conveying guide wire are improved, and the conveying and the releasing of the stent are favorably realized.
Generally, the maximum outer diameter of the second developing member 140 is approximately the same as or slightly smaller than the inner diameter of the delivery tube. The second imaging member 140 has a fourth proximal end and a fourth distal end opposite to each other, and typically, the mandrel 110 on the side of the fourth proximal end of the second imaging member 140 has an outer diameter smaller than the inner diameter of the delivery tube, so that a cavity exists between the mandrel 110 and the delivery tube. If the cavity is large, the second distal end of the mandrel 110 may be unstable during pushing of the pushwire 100, which increases the pushing resistance of the pushwire 100. In this regard, the mandrel 110 is adjusted to make the mandrel 110 adjacent to the fourth proximal end of the second developing element 140 be a variable diameter section, and a reducing spring 150 is sleeved on the variable diameter section, and the reducing spring 150 is connected to the second developing element 140. The filling of the cavity between the mandrel 110 and the delivery tube by the reducing spring 150 ensures the stability of the second distal end of the mandrel 110 during the pushing through and at the same time does not negatively affect the compliance of the mandrel 110.
Optionally, the second developing part 140 may include a body, a mounting through hole (not labeled in the figure) is axially disposed along the body, and a gap exists between a hole wall of a portion of the mounting through hole near the first proximal end and the mandrel 110 along a direction from the fourth proximal end to the fourth distal end, so that the distal end of the reducing spring 150 may be inserted into the second developing part 140, such that the reducing spring 150 is coaxial with the mandrel 110. In addition, for the embodiment of the present invention, along the direction from the second near end to the second far end, the interval between two adjacent spring coils in the reducing spring 150 is gradually increased (i.e. from the second near end to the direction from the second far end, the spring coils of the reducing spring 150 are more and more sparse), so that the second far end of the mandrel 110 can be ensured to have sufficient flexibility without affecting the transmission of the pushing force.
Fig. 3a to 3c show a second embodiment of the present invention, and only the differences between this embodiment and the first embodiment will be described below, and the descriptions of other structures that are the same as the first embodiment will be omitted. As shown in fig. 3a and 3b, the loading section L in the second embodiment of the present invention1The mandrel 110 has a plurality of discontinuous protrusions 111, the plurality of protrusions 111 are arranged at intervals along the axial direction of the mandrel 110, and the gap between two adjacent protrusions 111 is the recess 112.
Referring to fig. 3b, in one implementation of the present example, the membrane structure 120 is disposed only at the recess 112, and the protrusion 111 is used as a limiting mechanism to block the displacement of the membrane structure 120. It should be noted that the width of the recess 112 should not be too large, otherwise the film structure 120 can move in a small range, so that the width of the recess 112 in this embodiment is generally set to be between 0.5mm and 6mm, and preferably, the width of the recess 112 can be between 0.5mm and 4 mm. It is understood that the width of the recess refers to the distance between two adjacent protrusions in the axial direction of the mandrel.
Alternatively, referring to fig. 3c, in another implementation manner of the present embodiment, the membrane structure 120 may be disposed on the entire loading section L1In other words, the film structure 120 fills the concave portion 112 and covers the convex portion 111, and the film structure 120 furtherMay further extend on the side of said protrusion 111 at the edge facing away from said recess 112.
Further, in this embodiment, the outer diameters of the plurality of protrusions 111 decrease sequentially from the second proximal end to the second distal end to improve the compliance of the pushwire 100.
Fig. 4a and 4b show schematic views of a third embodiment of the present invention, and similarly, only the differences between the present embodiment and the first embodiment will be described below. Referring to fig. 4a and 4b, the mandrel 110 is arranged at the loading section L1Has a twisted structure formed by twisting, so that the loading section L is1Has a continuous spiral protrusion 111 and a continuous spiral depression 112. The kink structure can be formed by twisting in various ways, for example, fixing one end of the mandrel 110, heating the mandrel 110, rotating (twisting) the other end of the mandrel 110 around the axis of the mandrel 110, specifically, twisting 180 °, 360 ° or any other angle, and finally cooling and shaping; alternatively, the two ends of the mandrel 110 may be twisted simultaneously with heating, or may be twisted in opposite directions simultaneously, or the like. The membrane structure 120 may be disposed throughout the loading section L1Or the membrane structure is only arranged at the recess (not shown). The kinking structure can reduce the possibility of loosening, wrinkling, and displacement of the membrane structure 120, and can improve the twist control of the delivery guidewire 100 without increasing the loading section L1Affects the compliance of the pushwire 100. In addition, in the present embodiment, the number of turns of the helical projection 111 is designed according to the length of the stent to be delivered, that is, the longer the stent is, the more the number of turns of the projection 111 is.
Based on any kind of aforesaid transport seal wire, the embodiment of the utility model also provides a treatment device. Treatment device is including carrying seal wire, medical implant and conveyer pipe, the conveyer pipe has the inner chamber that the axial is link up, the inner chamber is used for holding medical implant, and the wall extrusion of inner chamber medical implant so that medical implant is compressed, after the compression medical implant suit is in on the membrane structure. The medical implant can be a self-expanding stent, a medical embolic coil, a vascular occlusion device, and the like.
Further, by embedding at least a portion of the membrane structure in a recess in the delivery guidewire, the outer diameter of the membrane structure may be reduced, thereby accommodating delivery tubes of different inner diameters, and thus the size of the lumen in this embodiment may be selected from a variety of sizes, such as, for example, a radial size of the lumen between 0.017 and 0.029 inches, or the radial size of the lumen may be smaller, such as, for example, a radial size of the lumen less than or equal to 0.027 inches, or even a radial size of the lumen less than or equal to 0.021 inches. The delivery tube with smaller size can reach a far-end blood vessel or a finer lesion part, and the treatment range is enlarged. Meanwhile, the whole flexibility of the treatment device is provided, the treatment device can reach the lesion part smoothly through roundabout blood vessels, and the success rate of the operation is improved.
Although the present invention is disclosed above, it is not limited thereto. Various modifications and alterations of this invention may be made by those skilled in the art without departing from the spirit and scope of this invention. Thus, if such modifications and variations of the present invention fall within the scope of the claims and their equivalents, the present invention is also intended to include such modifications and variations.
Claims (18)
1. A pushwire comprising a mandrel having a loading section formed with a plurality of projections around the mandrel in an axial direction of the mandrel, adjacent projections forming recesses therebetween, and a membrane structure disposed at least partially over the recesses.
2. The pushwire of claim 1, wherein said loading segment has a twisted configuration formed by twisting such that said loading segment has a continuous helical projection and a continuous helical depression thereon.
3. The pushwire of claim 1, wherein a plurality of said projections are spaced apart or adjacent to each other along the axial direction of said mandrel, each of said projections extending circumferentially around said mandrel.
4. The pushwire of any of claims 1-3, wherein said membrane structure fills said recess and covers the entire loading segment.
5. The pushwire of any of claims 1 to 3, wherein said membrane structure is provided in plurality, and a plurality of said membrane structures are provided in said recess; and/or the film structure is arranged on the side of the projection at the edge facing away from the recess.
6. The pushwire of any of claims 1-3, wherein the distance between two adjacent protrusions is between 0.5mm and 6 mm.
7. The pushwire of claim 6, wherein the distance between two adjacent protrusions is 0.5mm to 4 mm.
8. The pushwire of any of claims 1-3, wherein said mandrel has opposite proximal and distal ends, and wherein the outer diameter of said plurality of projections decreases sequentially in a direction from said proximal end to said distal end.
9. The pushwire of any of claims 1-3, wherein a transition is further disposed between said mandrel and said membrane structure, said transition being configured to hoop around said loading segment, and said transition having a void structure.
10. The pushwire of claim 9, wherein said transition is welded to said mandrel or said transition is bonded to said mandrel.
11. The pushwire of claim 9, wherein said transition portion comprises a plurality of coils arranged along an axial direction of said mandrel, said void structure being formed between two adjacent coils.
12. The pushwire of claim 9, wherein said transition portion is a helical structure formed by a wire helically wound around the axis of said mandrel, said void structure being formed between adjacent turns of said wire.
13. The pushwire of claim 9, wherein said transition portion is a tubular mesh structure woven from filaments, and wherein said voids of said tubular mesh structure form said void structure.
14. The pushwire of claim 9, wherein said transition portion is made of a metallic material, said metallic material being developable.
15. The pushwire of claim 1, wherein said membrane structure comprises any one or more of a thermoplastic elastomer, a thermoplastic polyurethane elastomer, silicone, nylon, and an acrylic polymer.
16. A treatment device comprising a delivery tube, a medical implant, and a delivery guidewire as defined in any one of claims 1-15, the delivery tube having an axially-extending lumen for receiving the medical implant, and a wall of the lumen compressing the medical implant to cause the medical implant to be compressed; the compressed medical implant is sleeved on the membrane structure.
17. The treatment apparatus of claim 16, wherein the medical implant is a self-expanding stent.
18. The treatment device of claim 16, wherein the lumen has a radial dimension in a range of 0.017 inches to 0.029 inches.
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| CN201922079500.XU CN211460698U (en) | 2019-11-27 | 2019-11-27 | Delivery guide wire and treatment device |
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| CN201922079500.XU CN211460698U (en) | 2019-11-27 | 2019-11-27 | Delivery guide wire and treatment device |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
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| CN113116449A (en) * | 2021-05-10 | 2021-07-16 | 杭州德诺脑神经医疗科技有限公司 | Delivery system and delivery guidewire thereof |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113116449A (en) * | 2021-05-10 | 2021-07-16 | 杭州德诺脑神经医疗科技有限公司 | Delivery system and delivery guidewire thereof |
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