Support imbedding device with electric cutting function

Abstract

The utility model provides a support imbedding device with an electric cutting function, and relates to the technical field of medical instruments. The stent implantation device with the electric cutting function comprises a puncture head and a conveying catheter, the puncture head comprises a cutting piece, the conveying catheter comprises an inner tube, and the cutting piece and the inner tube are both made of conductive materials. The inner tube comprises a far end and a near end, the cutting piece and the far end of the inner tube are fixedly connected in a non-glue-joint mechanical connection mode or an integrally-formed connection mode, and the cutting piece and the inner tube conduct electricity mutually. According to the stent implantation device with the electric cutting function, the cutting piece of the puncture head is fixedly connected with the inner tube in a non-glue-joint mechanical connection mode or an integrally-formed connection mode, the electric energy conduction process between the cutting piece and the catheter can be achieved, therefore, conductive metal wires are saved, glue does not need to be used, and the cost is reduced. The problems of connection failure caused by glue performance reduction and unexpected insulation, poor electric conduction and the like caused by glue overflow can be prevented.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, and in particular to a stent placement device with an electric cutting function. Background Technology

[0002] Currently, endoscopic ultrasound-guided anastomosis between various human organs is becoming increasingly widely used. During the anastomosis, a bypass is established using a double-flange-shaped stent to achieve the clinical purpose of internal drainage or subsequent instrumentation into the target organ.

[0003] However, since the use of instruments that directly use the delivery system to puncture, enlarge the hole, and release the stent in stages using the "one-step" method is more convenient, the use of stent delivery systems with electric cutting function has gradually become more widespread.

[0004] An existing stent delivery system with electric cutting function includes a puncture head and a conduit. The puncture head is formed by coiling a thin stainless steel wire around the surface of a tapered insulating component. The stainless steel wire serves as the cutting wire. A conductive thin copper wire is spot-welded to one side of the stainless steel wire. The thin copper wire passes through the inner tube of the conduit and is welded to a copper conductive plug at the rear end of the inner tube. A double-flange stent is installed between the inner and outer tubes of the conduit. The inner tube is fixed to the puncture head with adhesive. Thus, the stent can be released by pulling the outer tube backward. During the retraction of the outer tube, the two flanges on the stent can be released sequentially. To facilitate differentiation between the release of the front and rear flanges, the stent delivery system also has a groove on the operating handle at the rear end of the conduit to indicate the release status.

[0005] Another existing stent delivery system with electric cutting function uses a conical metal piece as the cutting head, and then an insulating component is glued to the outside of the cutting head to form a puncture head. A conductive metal wire is welded to one side of the cutting head, passing through the conduit to the rear end and welding it to a conductive plug. This stent delivery system also has a double-flange-shaped stent installed between the inner and outer tubes of the conduit, and its puncture head is also glued to the inner tube. Thus, this stent delivery system also achieves the step-by-step release of the front and rear flanges of the stent by pulling the outer tube backward. Furthermore, this stent delivery system uses colored blocks or non-transparent markings on the outer tube to indicate to the operator the release of the front and rear flanges of the stent.

[0006] However, in the two types of support delivery systems with electric cutting function mentioned above, the puncture head and the inner tube are fixed with glue. However, the performance of glue will decrease when it is exposed to high temperature or after aging, which will lead to connection failure. Moreover, the glue bonding process is complicated and is prone to glue overflow, which may cause unexpected failures such as poor insulation and conductivity. Utility Model Content

[0007] The purpose of this utility model is to provide a stent inserter with electric cutting function to alleviate the technical problems existing in the prior art where the puncture head and inner tube are fixed by glue. However, the performance of the glue will decrease after being exposed to high temperature or aging, resulting in connection failure. Furthermore, the gluing process is complicated and is prone to glue overflow, which may cause unexpected failures such as poor insulation and conductivity.

[0008] In a first aspect, this utility model provides a stent placement device with electric cutting function, including a puncture head and a delivery conduit;

[0009] The puncture head includes a cutting element, and the delivery conduit includes an inner tube. Both the cutting element and the inner tube are made of conductive materials.

[0010] The inner tube includes a distal end and a proximal end. The cutting element is fixedly connected to the distal end of the inner tube by a non-adhesive mechanical connection or an integrally formed connection, and the cutting element and the inner tube are electrically conductive to each other.

[0011] In an optional embodiment, the cutting element is fixedly connected to the distal end of the inner tube by any one of the mechanical connection methods of welding, interference fit, and riveting.

[0012] In an optional embodiment, the puncture head further includes an insulating component. The cutting component and the insulating component are fixedly connected by a non-adhesive mechanical connection or an integrally formed connection. Alternatively, the insulating component is fixedly connected to the distal end of the inner tube by a non-adhesive mechanical connection. The cutting component is a conductive coating applied to the insulating component.

[0013] In an optional embodiment, the insulating member is tubular and is sleeved over the cutting member, and a snap-fit ​​structure is provided between the inner wall of the insulating member and the outer wall of the cutting member;

[0014] The snap-fit ​​structure includes a slot and a snap-fit ​​protrusion. One of the slot and the snap-fit ​​protrusion is located on the inner wall of the insulating member, and the other is located on the outer wall of the cutting member. The snap-fit ​​protrusion snaps into the slot and abuts against the inner wall of the slot along the circumference of the insulating member.

[0015] In an optional embodiment, the puncture head further includes a limiting member, which is fixed to the side of the cutting member near the distal end of the inner tube by a non-adhesive mechanical connection, and a stepped portion is formed between the side of the limiting member away from the proximal end of the inner tube and the outer wall of the cutting member.

[0016] The end of the insulating element near the proximal end of the inner tube abuts against the stepped portion.

[0017] In an optional embodiment, the delivery conduit further includes a middle tube and an outer tube, wherein the middle tube is sleeved outside the inner tube and the outer tube is sleeved outside the middle tube;

[0018] Both the middle tube and the outer tube include a proximal end and a distal end. The distal end of the middle tube passes through the distal end of the outer tube and extends out of the outer tube. The section of the middle tube outside the outer tube is the operating area. The operating area is provided with a fixing structure. The fixing structure can move along the axial direction of the middle tube within the operating area and is fixed at any position in the operating area. When the fixing structure is fixed in the operating area, it abuts against the proximal end of the outer tube to restrict the movement of the outer tube in the direction close to the proximal end of the inner tube.

[0019] In an optional embodiment, the fixing structure includes a fixing sleeve and a limiting screw. The fixing sleeve is fitted outside the operating area of ​​the middle tube, and the fixing sleeve is provided with a threaded hole extending radially thereon. The limiting screw is threaded into the threaded hole and can abut against the outer wall of the middle tube in the operating area.

[0020] In an optional embodiment, the fixing structure further includes a rubber sleeve, which is fitted between the fixing sleeve and the central tube of the operating area.

[0021] In an optional embodiment, the inner tube has engraved patterns at least near its distal end.

[0022] In an optional embodiment, it further includes a first handle, a conductive plug, and a resilient element;

[0023] The first handle includes a socket portion with an internal cavity, one end of the conductive plug protruding outside the first handle, and the other end extending into the cavity of the socket portion;

[0024] The proximal end of the inner tube extends into the cavity of the socket portion;

[0025] The elastic element is located inside the socket and is electrically connected between the conductive plug and the inner tube, and the elastic element is in a compressed energy storage state.

[0026] This utility model provides a stent placement device with electro-cutting function, comprising a puncture head and a delivery conduit. The puncture head includes a cutting component, and the delivery conduit includes an inner tube. Both the cutting component and the inner tube are made of conductive materials. The inner tube includes a distal end and a proximal end. The cutting component and the distal end of the inner tube are fixedly connected by a non-adhesive mechanical connection or an integrally formed connection, and the cutting component and the inner tube are mutually conductive. This utility model provides a stent placement device with electro-cutting function, applicable to anastomosis between organs such as the human digestive tract. It can also deliver a double-flange-shaped stent to the target organ via the delivery conduit and perform puncture using the puncture head. Unlike existing stent delivery systems with electro-cutting function, the cutting component in the puncture head of this utility model is fixedly connected to the inner tube by a non-adhesive mechanical connection or an integrally formed connection. Non-adhesive mechanical connection methods include welding, interference fit, riveting, etc. Because the cutting component and the inner tube are not bonded with adhesive, no glue is needed at the connection point. This eliminates the performance degradation caused by glue being exposed to high temperatures or aging, thus preventing glue connection failure and effectively extending the service life of both the cutting component and the inner tube. Furthermore, since no glue is needed, there is no glue overflow at the connection point, effectively preventing unexpected insulation or conductivity problems. Moreover, both the cutting component and the inner tube in this invention are made of conductive materials, allowing them to conduct electricity to each other after being fixedly connected. This allows direct power supply to the cutting component via the inner tube to achieve its electric cutting function, eliminating the need for an additional conductive wire on one side of the cutting component. This not only saves materials but also simplifies the structure and reduces processing steps.

[0027] Compared with the prior art, the stent inserter with electric cutting function provided by this utility model can not only realize the electrical energy conduction process between the cutting part and the conduit by fixing the cutting part of the puncture head and the inner tube through a non-adhesive mechanical connection or an integral molding connection, thus saving conductive metal wire, but also eliminates the need for glue, preventing connection failure due to glue performance degradation and preventing problems such as unexpected insulation and poor conductivity caused by glue overflow. Attached Figure Description

[0028] To more clearly illustrate the specific embodiments of this utility model or the technical solutions in the prior art, the drawings used in the description of the specific embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of this utility model. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0029] Figure 1A schematic diagram of the structure of the bracket inserter with electric cutting function provided in this embodiment of the utility model;

[0030] Figure 2 A cross-sectional view of the cutting component, insulating component, limiting component, and partial inner tube provided in an embodiment of this utility model;

[0031] Figure 3 A cross-sectional view of a conductive plug, conductive component, socket portion, and partial inner tube provided in an embodiment of this utility model.

[0032] Icons: 1-Piercing head; 10-Cutting component; 11-Insulating component; 12-Limiting component; 120-Step section; 2-Delivery conduit; 20-Inner tube; 21-Middle tube; 210-Operating area; 22-Outer tube; 3-Fixing structure; 30-Fixing sleeve; 31-Limiting screw; 4-Positioning component; 5-First handle; 50-Socket section; 6-Conductive plug; 7-Elastic component; 8-Second handle; 80-Safety lock; 9-Connecting post. Detailed Implementation

[0033] To make the objectives, technical solutions, and advantages of the embodiments of this utility model clearer, the technical solutions of the embodiments of this utility model will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this utility model, and not all embodiments. The components of the embodiments of this utility model described and shown in the accompanying drawings can generally be arranged and designed in various different configurations.

[0034] Therefore, the following detailed description of the embodiments of the present invention provided in the accompanying drawings is not intended to limit the scope of the claimed invention, but merely to illustrate selected embodiments of the invention. All other embodiments obtained by those skilled in the art based on the embodiments of the present invention without inventive effort are within the scope of protection of the present invention.

[0035] The following detailed description, in conjunction with the accompanying drawings, outlines some embodiments of the present invention. Unless otherwise specified, the following embodiments and features can be combined with each other.

[0036] Example:

[0037] like Figures 1-2 As shown, the stent placement device with electric cutting function provided in this embodiment includes a puncture head 1 and a delivery conduit 2; the puncture head 1 includes a cutting element 10, and the delivery conduit 2 includes an inner tube 20. Both the cutting element 10 and the inner tube 20 are made of conductive materials; the inner tube 20 includes a distal end and a proximal end. The cutting element 10 and the distal end of the inner tube 20 are fixedly connected by a non-adhesive mechanical connection or an integrally formed connection, and the cutting element 10 and the inner tube 20 are electrically conductive to each other.

[0038] The stent placement device with electrocautery function provided in this embodiment is used in anastomosis between organs such as the human digestive tract. It can deliver a double-flange-shaped stent to the target organ via the delivery catheter 2, and perform puncture using the puncture head 1. During the use of this electrocautery stent placement device, after selecting the puncture site, the delivery catheter 2 can be advanced to the target organ using a guidewire or endoscope. Then, the inner tube 20 is energized, thereby energizing the cutting element 10, which can then cut the target organ such as the human digestive tract tissue. To reduce the risk of cutting the guidewire, the distal end of the inner tube 20 can be provided with a rounded chamfer.

[0039] Unlike existing stent delivery systems with electric cutting capabilities, the cutting element 10 in the piercing head 1 of the stent inserter with electric cutting capability provided in this embodiment is fixedly connected to the inner tube 20 via a non-adhesive mechanical connection or an integrally formed connection. Non-adhesive mechanical connection methods include welding, interference fit, and riveting. Because the cutting element 10 and the inner tube 20 are not glued together, no glue is needed at the connection point, preventing performance degradation caused by glue being exposed to high temperatures or aging, thus preventing glue connection failure and effectively extending the service life of the cutting element 10 and the inner tube 20. Furthermore, since no glue is needed, there is no glue overflow at the connection point between the cutting element 10 and the inner tube 20, effectively preventing unexpected potential failures such as poor insulation or conductivity at the connection point.

[0040] Furthermore, in this embodiment, both the cutting element 10 and the inner tube 20 are made of conductive materials, such as stainless steel, copper, and other conductive metals. After the cutting element 10 and the inner tube 20 are fixedly connected, they can conduct electricity to each other. Thus, the inner tube 20 can be directly connected to an external power source to energize the cutting element 10, thereby realizing the electric cutting function of the cutting element 10. There is no need to set an additional conductive metal wire on one side of the cutting element 10, which not only saves materials but also simplifies the structure and reduces processing steps.

[0041] Compared with the prior art, the stent placement device with electric cutting function provided in this embodiment fixes the cutting part 10 of the puncture head 1 and the inner tube 20 through a non-adhesive mechanical connection or an integral molding connection. This not only realizes the electrical energy conduction process between the cutting part 10 and the conduit, thereby saving conductive metal wire, but also eliminates the need for glue, preventing connection failure due to glue performance degradation and preventing problems such as unexpected insulation and poor conductivity caused by glue overflow.

[0042] There are various non-adhesive mechanical connection methods. In order to ensure the connection stability between the cutting part 10 and the inner tube 20, this embodiment preferably uses any one of the mechanical connection methods of welding, interference fit and riveting to fix the far end of the cutting part 10 and the inner tube 20.

[0043] Furthermore, such as Figure 1 As shown, the piercing head 1 also includes an insulating element 11. The cutting element 10 and the insulating element 11 are fixedly connected by a non-adhesive mechanical connection or an integrally formed connection. Alternatively, the insulating element 11 is fixedly connected to the distal end of the inner tube 20 by a non-adhesive mechanical connection. The cutting element 10 is a conductive coating applied to the insulating element 11.

[0044] Compared to existing support conveying systems that use adhesive to fix insulating components to cutting components, in this embodiment, the insulating component 11 is fixedly connected to the cutting component 10 via a non-adhesive mechanical connection or an integrally formed connection. This also avoids the use of adhesive, preventing adhesive performance degradation or overflow. When the cutting component 10 has a conductive coating applied to the insulating component 11, the cutting component 10 can be fixedly connected to the distal end of the inner tube 20 via the insulating component 11. In this case, again to avoid using adhesive, the insulating component 11 must be fixedly connected to the distal end of the inner tube 20 via a non-adhesive mechanical connection.

[0045] Among them, the insulating part 11 is made of insulating materials such as zirconium oxide. Both the insulating part 11 and the cutting part 10 can be formed by powder metallurgy forming, machining or stamping. During the processing, the insulating part 11 and the cutting part 10 can also be integrally formed by insert forming process.

[0046] In this embodiment, the cutting component 10 and the insulating component 11 are preferably fixedly connected by a non-adhesive mechanical connection. In this case, the insulating component 11 can be tubular and sleeved on the outside of the cutting component 10. A snap-fit ​​structure is provided between the inner wall of the insulating component 11 and the outer wall of the cutting component 10. The snap-fit ​​structure includes a slot and a snap-fit ​​protrusion. One of the slot and the snap-fit ​​protrusion is provided on the inner wall of the insulating component 11, and the other is provided on the outer wall of the cutting component 10. The snap-fit ​​protrusion snaps into the slot and abuts against the inner wall of the slot along the circumference of the insulating component 11.

[0047] Both the slot and the snap-fit ​​protrusion can extend along the axial direction of the insulating member 11. During use, the slot and the snap-fit ​​protrusion in the snap-fit ​​structure can cooperate with each other to restrict the rotation of the insulating member 11 sleeved outside the cutting member 10, preventing the insulating member 11 from rotating outside the cutting member 10 and affecting its stability.

[0048] It should be noted that, to ensure the cutting function of the cutting component 10, the cutting component 10 must have a cutting portion exposed outside the insulating component 11. When the insulating component 11 is fitted over the cutting component 10, such as Figure 2As shown, the end of the cutter 10 away from the inner tube 20 can extend out of the insulator 11.

[0049] Furthermore, the cutting element 10 may include a plurality of cutting wings, which are distributed circumferentially along the insulating element 11 and each cutting wing extends axially along the insulating element 11.

[0050] When the insulating member 11 is sleeved outside the cutting member 10, in order to improve the overall strength of the piercing head 1, this embodiment preferably fills the gap between the cutting member 10 and the insulating member 11 with a soft material layer, such as a silicone layer.

[0051] To further improve the overall stability of the puncture head 1, such as Figure 2 As shown, in this preferred embodiment, the puncture head 1 also includes a limiting member 12. The limiting member 12 is fixed to the side of the cutting member 10 near the far end of the inner tube 20 by a non-adhesive mechanical connection, and a step portion 120 is formed between the side of the limiting member 12 away from the near end of the inner tube 20 and the outer wall of the cutting member 10; the end of the insulating member 11 near the near end of the inner tube 20 abuts against the step portion 120.

[0052] During use, since the end of the insulating member 11 near the proximal end of the inner tube 20 abuts against the step portion 120, the limiting member 12 can restrict the insulating member 11 from moving along its own axial direction towards the proximal end of the inner tube 20. At this time, the axial movement freedom of the insulating member 11 is restricted. Combined with the above-mentioned locking structure's restriction on the rotation of the insulating member 11, the stability of the insulating member 11 on the cutting member 10 can be effectively guaranteed.

[0053] The limiting member 12 can be fixedly connected to the cutting member 10 by any of the mechanical connection methods such as welding, riveting, or interference fit. In order to facilitate the connection between the limiting member 12 and the cutting member 10, it is preferred in this embodiment that the material of the limiting member 12 is the same as that of the cutting member 10. Based on this, the material of the limiting member 12 can also be a metal material such as stainless steel.

[0054] In this embodiment, the cutting part 10, insulating part 11, and limiting part 12 of the piercing head 1 can also be formed by an integral molding process. At this time, the overall structural stability of the piercing head 1 is optimal, which can effectively improve the performance of the piercing head 1.

[0055] like Figure 1As shown, the delivery conduit 2 also includes a middle tube 21 and an outer tube 22. The middle tube 21 is sleeved outside the inner tube 20, and the outer tube 22 is sleeved outside the middle tube 21. Both the middle tube 21 and the outer tube 22 include a proximal end and a distal end. The distal end of the middle tube 21 passes through the distal end of the outer tube 22 and extends out of the outer tube 22. The tube body of the middle tube 21 located outside the outer tube 22 is the operating area 210. The operating area 210 is provided with a fixing structure 3. The fixing structure 3 can move along the axial direction of the middle tube 21 within the operating area 210 and be fixed at any position in the operating area 210. When the fixing structure 3 is fixed in the operating area 210, it abuts against the proximal end of the outer tube 22 to restrict the movement of the outer tube 22 in the direction close to the proximal end of the inner tube 20.

[0056] It should be noted that the proximal and distal ends of the inner tube 20, middle tube 21, and outer tube 22 are based on the position of the delivery catheter 2 relative to the operator. Specifically, the end of the inner tube 20, middle tube 21, and outer tube 22 closer to the operator is the proximal end, and the end farther from the operator, that is, the end used to enter the patient's body, is the distal end.

[0057] To prevent the entire delivery conduit 2 from becoming electrified, the inner tube 20 needs to be insulated after being energized. Therefore, in this embodiment, the middle tube 21 is made of insulating materials such as plastic, while the outer tube 22 only needs to have an insulating layer on its inner wall. Furthermore, the outer tube 22 can be made of a single material or a composite material including a metal mesh tube.

[0058] It should be noted that a double-flange support is usually installed inside the delivery conduit 2. The installation location of the support is summarized below: Figure 1 As shown, the distal end of the inner tube 20 passes through the distal end of the middle tube 21 and extends outside the middle tube 21. The distal ends of the inner tube 20 and the outer tube 22 are flush. A support is installed in the space between the distal ends of the inner tube 20, the distal ends of the middle tube 21, and the inner wall of the outer tube 22. The support includes distal flanges and proximal flanges that are spaced apart along the axial direction of the delivery conduit 2. The distal flanges and proximal flanges form a double flange of the support. The distal flange is close to the distal end of the inner tube 20, and the proximal flange is far away from the distal end of the inner tube 20.

[0059] like Figure 1 As shown, a positioning element 4 may be provided on the tube body of the inner tube 20 located between its distal end and the distal end of the middle tube 21, and the bracket is fixed to the tube body of the inner tube 20 by the positioning element 4.

[0060] The stent placement device with electric cutting function provided in this embodiment is used to deliver the stent to the target organ. After the stent is delivered to the position, the distal flange and proximal flange on the stent need to be released so that the distal flange and proximal flange abut against the target organ and the organ adjacent to the target organ, respectively. This allows the distal flange and proximal flange to form stable support for the puncture head 1, which facilitates subsequent cutting operations.

[0061] To release the distal and proximal flanges on the support, the outer tube 22 can typically move axially relative to the middle tube 21. When releasing the support, the outer tube 22 can be pulled towards the proximal end of the inner tube 20, causing the distal end of the outer tube 22 to move away from the distal end of the inner tube 20. During this movement, the distal flange of the support will be exposed first; that is, the distal flange of the support will be released first by the outer tube 22. Continuing to pull the outer tube 22 towards the proximal end of the inner tube 20 will also release the proximal flange of the support.

[0062] It should be noted that, in order to facilitate operators in distinguishing between the release of the near and far flanges of the support, the existing support delivery system uses color blocks or non-transparent markings on the outer pipe for indication. However, for inexperienced operators, it is easy to release both the near and far flanges of the support at once, causing the near flange to be released prematurely and unable to be fixed in the expected position, which can lead to serious consequences.

[0063] In this embodiment, by setting up a fixing structure 3, after the distal flange of the support is released from the outer tube 22, the proximal end of the outer tube 22 abuts against the fixing structure 3, thereby restricting further movement of the outer tube 22. At this point, only by separating the fixing structure 3 from the middle tube 21 and then moving the fixing structure 3 on the middle tube 21 towards the proximal end of the inner tube 20 can space be made for the proximal end of the outer tube 22, allowing the outer tube 22 to continue moving towards the proximal end of the inner tube 20 and releasing the proximal flange. Therefore, even for inexperienced operators, this embodiment, through the physical locking structure of the fixing structure 3, can still clearly distinguish between the release of the distal and proximal flanges.

[0064] It should be noted that, since the fixing structure 3 provided in this embodiment can move along the axial direction of the central tube 21 within the operating area 210 and be fixed at any position in the operating area 210, adjusting the initial fixing position of the fixing structure 3 in the operating area 210 will ensure that the fixing structure 3 does not affect the release process of the distal flange of the support, while also limiting the premature release of the proximal flange of the support. Specifically, the initial fixing position of the fixing structure 3 in the operating area 210 can be the middle of the operating area 210.

[0065] It should also be noted that the fixing structure 3 can move along the axial direction of the middle tube 21 within the operating area 210. This not only makes it easier for the fixing structure 3 to make way for the continued movement of the outer tube 22, but also makes it easier to adjust the initial fixing position of the fixing structure 3 in the operating area 210 according to the brackets of different sizes, thereby improving the application range of the fixing structure 3.

[0066] There are no restrictions on the connection method between the fixed structure 3 and the operating area 210 of the middle tube 21, as long as the fixed structure 3 and the operating area 210 of the middle tube 21 are detachably connected. For example, the fixed structure 3 can be a clamp.

[0067] Or, such as Figure 1 As shown, the fixing structure 3 may include a fixing sleeve 30 and a limiting screw 31. The fixing sleeve 30 is sleeved outside the operating area 210 of the middle tube 21, and the fixing sleeve 30 is provided with a threaded hole extending radially thereon. The limiting screw 31 is threaded into the threaded hole and can abut against the outer wall of the middle tube 21 of the operating area 210.

[0068] During use, by turning the limiting screw 31 toward the middle tube 21, the tube body of the operating area 210 of the middle tube 21 is radially squeezed by the limiting screw 31, thereby increasing the friction between the limiting screw 31 and the middle tube 21, tightening the operating area 210 of the middle tube 21, and effectively ensuring the stability of the fixing structure 3 at this position.

[0069] Furthermore, the fixing structure 3 may also include a rubber sleeve, which is fitted between the fixing sleeve 30 and the central tube 21 of the operating area 210.

[0070] The rubber sleeve is used to increase the friction between the fixing structure 3 and the middle tube 21, thereby further improving the positional stability of the fixing structure 3.

[0071] In this embodiment, to ensure the installation space of the stent, when the axial length of the puncture head 1 is less than 10mm, the axial distance between the side of the insulating member 11 near the proximal end of the inner tube 20 and the side of the cutting member 10 near the proximal end of the inner tube 20 can be no more than 2mm. At this time, the limiting member 12 will not occupy too much space on the proximal periphery of the inner tube 20, thereby providing more accommodating area for the stent.

[0072] It should also be noted that, such as Figure 1 As shown, a second handle 8 can be fixed to the near end of the outer tube 22. The second handle 8 makes it easy for the user to pull the outer tube 22 to release the near and far flanges of the bracket, effectively improving the ease of use of the bracket inserter with electric cutting function.

[0073] Furthermore, a safety lock 80 may be provided on the side of the second handle 8 near the fixing structure 3. The safety lock 80 is used to fix or separate the second handle 8 from the central tube 21, thereby locking or unlocking the position of the second handle 8. In this embodiment, the safety lock can be the safety lock on an existing support conveying system. Since the safety lock is existing technology, its specific structure will not be described in detail here.

[0074] In this embodiment, the inner tube 20 has engraved patterns at least near its distal end.

[0075] Since the engraved texture makes the inner tube 20 easier to bend, thereby improving its bending performance, this embodiment preferably has engraved texture at least near its distal end. In this case, at least the distal end of the inner tube 20 with the puncture head 1 is easier to bend, thereby making it easier for the puncture head 1 to reach the target organ.

[0076] When the entire inner tube 20 has engraved patterns, the inner tube 20 can be made entirely of engraved tube.

[0077] Furthermore, the inner tube 20 can also be covered with a film layer, and the engraved patterns are set on the film layer. Correspondingly, the inner tube 20 can be a film-coated engraved tube.

[0078] like Figure 1 and Figure 3 As shown, the bracket inserter with electric cutting function provided in this embodiment may further include a first handle 5, a conductive plug 6, and a conductive component; the first handle 5 includes a socket portion 50 with an internal cavity, one end of the conductive plug 6 is exposed outside the first handle 5, and the other end extends into the cavity of the socket portion 50; the proximal end of the inner tube 20 extends into the cavity of the socket portion 50; the conductive component is located inside the socket portion 50 and is electrically connected between the conductive plug 6 and the inner tube 20.

[0079] The first handle 5 is an operating handle, and the conductive plug 6 is used for electrical connection with an external power source. It should be noted that the first handle 5 and the conductive plug 6 are inherent structures on existing stent delivery systems. Unlike existing stent delivery systems, which typically use conductive metal wires in the inner tube to achieve electrical connection between the conductive plug and the puncture head, the inner tube 20 in this embodiment is conductive. Furthermore, in this embodiment, the conductive plug 6 and the puncture head 1 can be electrically connected by electrically connecting a conductive element between the conductive plug 6 and the inner tube 20.

[0080] The conductive plug 6 can be fixed to the socket part 50 by means of threaded connection or other methods. The conductive component can be made of metal wire, conductive sheet or other structures, and the conductive component can be connected between the conductive plug 6 and the inner tube 20 by means of welding, crimping or overlapping.

[0081] In this embodiment, the conductive component is preferably an elastic component 7, and the elastic component 7 is in a compressed and energy-storing state between the conductive plug 6 and the inner tube 20. At this time, the conductive plug 6 and the inner tube 20 will apply an axial compressive force to the elastic component 7, thereby effectively ensuring the connection effect of the elastic component 7 between the conductive plug 6 and the inner tube 20.

[0082] Furthermore, the elastic element 7 can be a spring, to improve the connection stability between the spring and the conductive plug 6 and the inner tube 20, such as... Figure 3As shown, the conductive plug 6 may have a groove on the side near the spring, and the end of the spring near the conductive plug 6 extends into this groove. Furthermore, as... Figure 3 As shown, the inner tube 20 located inside the socket part 50 may be provided with a connecting post 9. The end of the spring near the inner tube 20 is sleeved on the connecting post 9. The connecting post 9 can support and limit the spring, further enhancing the connection reliability of the spring.

[0083] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of this utility model, and are not intended to limit it. Although the utility model has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some or all of the technical features therein. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of this utility model.

Claims

1. A stent-implanter with an electrically cutting function, characterized by, The puncture head (1) and the delivery catheter (2) are provided. The puncture head (1) comprises a cutting member (10), and the delivery catheter (2) comprises an inner tube (20), the cutting member (10) and the inner tube (20) are made of conductive material. The inner tube (20) comprises a distal end and a proximal end, the cutting member (10) is fixedly connected with the distal end of the inner tube (20) by a non-gluing mechanical connection mode or an integrated connection mode, and the cutting member (10) and the inner tube (20) are conductive to each other.

2. The charged cutting function stent placer of claim 1, wherein, The cutting member (10) and the distal end of the inner tube (20) are fixedly connected by any one of a mechanical connection mode of welding, interference fit and riveting.

3. The charged cutting function stent-siiter of claim 1, wherein, The puncture head (1) further comprises an insulating member (11), the cutting member (10) and the insulating member (11) are fixedly connected by a non-gluing mechanical connection mode or an integrated connection mode, or the insulating member (11) is fixedly connected with the distal end of the inner tube (20) by a non-gluing mechanical connection mode, and the cutting member (10) is a conductive coating coated on the insulating member (11).

4. The charged cutting function stentriever of claim 3, wherein, The insulating member (11) is tubular and is sleeved on the cutting member (10), and a clamping structure is arranged between the inner wall of the insulating member (11) and the outer wall of the cutting member (10). The clamping structure comprises a clamping groove and a clamping protrusion, one of the clamping groove and the clamping protrusion is arranged on the inner wall of the insulating member (11), and the other is arranged on the outer wall of the cutting member (10), the clamping protrusion is clamped in the clamping groove and abuts against the inner wall of the clamping groove along the circumferential direction of the insulating member (11).

5. The charged cutting function stent-siiter of claim 4, wherein, The puncture head (1) further comprises a limiting member (12), the limiting member (12) is fixedly connected to one side of the cutting member (10) close to the distal end of the inner tube (20) by a non-gluing mechanical connection mode, and a stepped portion (120) is formed between the side of the limiting member (12) away from the proximal end of the inner tube (20) and the outer wall of the cutting member (10). The end of the insulating member (11) close to the proximal end of the inner tube (20) abuts against the stepped portion (120).

6. The charged cutting function stent-sizer of any of claims 1-5, wherein, The delivery catheter (2) further comprises a middle tube (21) and an outer tube (22), the middle tube (21) is sleeved on the inner tube (20), and the outer tube (22) is sleeved on the middle tube (21). The middle tube (21) and the outer tube (22) each comprise a proximal end and a distal end, the distal end of the middle tube (21) extends out of the outer tube (22) after passing through the distal end of the outer tube (22), and the tube body of the middle tube (21) outside the outer tube (22) is an operation area (210); the operation area (210) is provided with a fixing structure (3), the fixing structure (3) can move along the axial direction of the middle tube (21) in the operation area (210) and is fixed at any position of the operation area (210), and the fixing structure (3) is used for abutting against the proximal end of the outer tube (22) when it is fixed at the operation area (210) to limit the movement of the outer tube (22) in the direction close to the proximal end of the inner tube (20).

7. The charged cutting function stent-siiter of claim 6, wherein, The fixing structure (3) comprises a fixing sleeve (30) and a limiting screw (31), the fixing sleeve (30) is sleeved outside the operation area (210) of the middle tube (21), and a threaded hole extending in the radial direction of the fixing sleeve (30) is arranged on the fixing sleeve (30); the limiting screw (31) is threadedly connected in the threaded hole and can abut against the outer wall of the middle tube (21) of the operation area (210).

8. The charged cutting function stent-siiter of claim 7, wherein, The fixing structure (3) further comprises a rubber sleeve, which is sleeved between the fixing sleeve (30) and the middle tube (21) of the operation area (210).

9. The charged cutting function stent-sizer of any of claims 1-5, wherein, At least the tube body near the distal end of the inner tube (20) is provided with engraved lines.

10. The charged cutting function stent-siiter of any of claims 1-5, wherein, Further comprising a first handle (5), a conductive plug (6) and an elastic member (7); The first handle (5) comprises a socket portion (50) with a cavity inside, one end of the conductive plug (6) is exposed outside the first handle (5), and the other end extends into the cavity of the socket portion (50); The proximal end of the inner tube (20) extends into the cavity of the socket portion (50); The elastic member (7) is located in the socket portion (50) and is electrically connected between the conductive plug (6) and the inner tube (20), and the elastic member (7) is in a compressed energy storage state.

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