Coronary artery bifurcation lesion implantation rear ridge stent beam optimization and parallel placement catheter

Abstract

The utility model belongs to the technical field of medical instruments, and discloses a coronary artery bifurcation lesion implantation rear ridge support beam optimized juxtaposition catheter which comprises a micro catheter, the micro catheter comprises a main catheter and two branch catheters, one ends of the two branch catheters are fixedly arranged at one end of the main catheter in a communicated mode, and a gap is formed between the two branch catheters; propelling assemblies are arranged on the surfaces of the main catheter and the two branch catheters; a large arc convex ring is arranged on the surface of the main catheter and located on one side of the branch catheters, and small arc convex rings are arranged on the sides, away from the main catheter, of the two branch catheters. In conclusion, the device has the advantages that the catheter can be firmly fixed in the blood vessel and cannot move, and meanwhile, the stent can be finely adjusted by means of the arrangement of the surface of the catheter.

Description

Technical Field

[0001] This utility model belongs to the field of medical device technology, specifically an optimized and paralleled catheter for the implantation of a stent beam after coronary artery bifurcation lesion. Background Technology

[0002] Coronary artery bifurcation lesions refer to narrowing of the coronary artery adjacent to and / or involving the openings of important branch vessels. Due to increased blood flow eddies and shear forces at the bifurcation point, atherosclerosis is more likely to occur. These lesions typically occur at the openings of important branches of the coronary arteries, such as the left main coronary artery, the left anterior descending artery, and the right coronary artery.

[0003] For example, patent number CN202023216819.1 describes an optimized and paralleled catheter device for stent beam placement after stent implantation in coronary artery bifurcation lesions. This device includes a microcatheter, a push rod, and a handle connected in sequence. The microcatheter is Y-shaped and includes a main tube and two bifurcation branches. The end of the main tube furthest from the push rod branches into the two bifurcation branches. However, this device has the following shortcomings in practical use:

[0004] Because the smooth surface of the catheter limits the amount of compression it can exert on the lesion in the blood vessel, the initial dilation of the blood vessel is not sufficient, which affects the subsequent placement of the stent and also makes the catheter not stable enough in the blood vessel.

[0005] Meanwhile, the smooth surface of the catheter does not allow for further fine-tuning of the stent beam position. A guidewire needs to be inserted into the stent hole for fine-tuning. However, the stent hole is not clearly visible on X-ray, making it difficult for the guidewire to efficiently adjust the stent beam. Summary of the Invention

[0006] To address the problems mentioned in the background art, this utility model provides an optimized and paralleled catheter for the ridge stent beam after implantation of coronary artery bifurcation lesions, which has the advantage of firmly fixing the catheter in the blood vessel without causing movement.

[0007] To achieve the above objectives, the present invention provides the following technical solution: a coronary artery bifurcation lesion posterior crest stent beam optimized placement catheter, including a microcatheter, wherein the microcatheter includes a main tube and two branch tubes, one end of the two branch tubes is connected and fixed to one end of the main tube, and a gap is provided between the two branch tubes;

[0008] The surfaces of the main tube and the two branch tubes are all provided with propulsion components;

[0009] The main tube surface has a large arc-shaped convex ring on one side of the branch tube, and the two branch tubes have small arc-shaped convex rings on the side away from the main tube.

[0010] Preferably, the propulsion components on the surfaces of the main tube and the two branch tubes have the same structure but different dimensions. The propulsion components include annular grooves formed on the surfaces of the main tube and the two branch tubes, and the outer edges of the annular grooves are provided with arc-shaped chamfers.

[0011] Preferably, a silicone ring is embedded in the surface of the main tube and the two branch tubes, located at the bottom of the inner cavity of the annular groove, and the outer side of the silicone ring is flush with the bottom of the inner cavity of the annular groove.

[0012] Preferably, the surface of the main guide tube is integrally formed with the large arc convex ring, and the branch guide tube is integrally formed with the small arc convex ring, with the small arc convex rings on the surfaces of the two branch guide tubes corresponding to each other.

[0013] Preferably, the large circular arc convex ring and the small circular arc convex ring protrude from the surface of the main tube and the two branch tubes, respectively.

[0014] Preferably, the openings of the two branch tubes are provided with an outer inclined surface near the outermost propulsion component, and the inner walls of the openings of the two branch tubes are provided with inner inclined surfaces with opposite outer inclined surfaces and the same slope.

[0015] Preferably, the main tube is integrally formed with a flow guide at one end of the two branch catheters, and the flow guide is integrally formed with one end of the two branch catheters. The position of the flow guide between the two branch catheters is set in an arc shape to avoid damage to the intersection of blood vessels, and the flow guide is conical in shape.

[0016] Compared with the prior art, the beneficial effects of this utility model are as follows:

[0017] 1. The large and small circular arc convex rings can expand their respective blood vessels. The diameter is larger than that of the main catheter and branch catheter, resulting in better expansion effect. This widens the expansion area, making it easier to place the stent beam later. At the same time, the better fit with the blood vessel will cause the blood vessel to expand slightly. Even if the user does not operate the microcatheter, the microcatheter will not move under the reaction force of the blood vessel.

[0018] 2. Push one end of the microcatheter's stent beam into the annular groove. This makes it easier to insert one end of the stent beam into the annular groove. Because the stent beam has a small diameter and a large arc-shaped convex ring, only one side of the stent beam can be pushed for fine adjustment, allowing the stent beam to be further adjusted to the appropriate position at the vascular lesion site. Attached Figure Description

[0019] Figure 1 This is a schematic diagram of the isometric structure of this utility model;

[0020] Figure 2 This is a top view of the structure of this utility model;

[0021] Figure 3 This utility model Figure 2 A schematic diagram of the structure at point B;

[0022] Figure 4 This utility model Figure 1 A schematic diagram of the structure at point A.

[0023] In the diagram: 1. Microcatheter; 11. Main tube; 2. Large circular arc convex ring;

[0024] 3. Propulsion assembly; 31. Annular groove; 32. Silicone ring;

[0025] 4. Flow deflector; 5. Branch duct; 6. Small arc convex ring; 7. Outer bevel; 8. Inner bevel. Detailed Implementation

[0026] The technical solutions of the present utility model will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only some embodiments of the present utility model, and not all embodiments. Based on the embodiments of the present utility model, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the protection scope of the present utility model.

[0027] like Figures 1 to 4 As shown, this utility model provides an optimized parallel catheter for implanting a stent beam after coronary artery bifurcation lesion, including a microcatheter 1. The microcatheter 1 is a parallel catheter, which includes a main tube 11 and two branch tubes 5. The length of the microcatheter 1 is 14-30cm, and the length of the two branch tubes 5 is 1-3.5cm. The specific length can be made according to actual needs. The outer diameter of the main tube 11 is 2.5-7mm, and the inner diameter is 2-6.5mm.

[0028] The outer diameter of the two branch catheters is 1.2–3.4 mm, and the inner diameter is 0.75–2.9 mm.

[0029] Two branch conduits 5 are connected at one end and fixed at one end of the main tube 11, and a gap is provided between the two branch conduits 5, the gap being 0.1 to 0.2 mm.

[0030] It should be noted that there are many different specifications and sizes when manufacturing catheters for actual surgery. The parameters listed in this case are for reference only, and customization is required according to actual needs.

[0031] The surfaces of the main tube 11 and the two branch catheters 5 are all provided with a propulsion component 3. The propulsion components 3 on the surfaces of the main tube 11 and the two branch catheters 5 have the same structure but different sizes. The propulsion component 3 includes annular grooves 31 formed on the surfaces of the main tube 11 and the two branch catheters 5. The depth of the annular grooves 31 is one-third of the wall thickness of the main tube 11 and the two branch catheters 5. The outer edges of the annular grooves 31 are provided with arc-shaped chamfers. The arc-shaped chamfers make the outer edges of the annular grooves 31 smooth, which can avoid scratching blood vessels. The surface of the main tube 11 is integrally formed with the large arc-shaped convex ring 2, and the branch catheters 5 are integrally formed with the small arc-shaped convex rings 6. The small arc-shaped convex rings 6 on the surfaces of the two branch catheters 5 correspond to each other.

[0032] A large arc-shaped protruding ring 2 is provided on the surface of the main tube 11 on one side of the branch tube 5, and a small arc-shaped protruding ring 6 is provided on the side of the two branch tubes 5 away from the main tube 11.

[0033] Specifically, the large arc convex ring 2 and the small arc convex ring 6 protrude from the surfaces of the main tube 11 and the two branch catheters 5, respectively. The distance between the outer apex of the small arc convex ring 6 and the large arc convex ring 2 and the surfaces of the main tube 11 and the two branch catheters 5 is 0.05 to 0.1 mm. When the small arc convex ring 6 is at its maximum protrusion distance, the surfaces of the two small arc convex rings 6 abut against each other. The small arc convex ring 6 and the large arc convex ring 2 are designed to increase the fit between the main tube 11 and the two branch catheters 5 and the blood vessel, and to prevent the main tube 11 and the two branch catheters 5 from moving in the blood vessel when there is no external force.

[0034] Furthermore, the openings of the two branch catheters 5 are provided with an outer inclined surface 7 near the outermost advancement component 3, which is inclined towards the center of the branch catheter 5. The inclination of the outer inclined surface 7 is 0.03~0.05 degrees. The inner walls of the openings of the two branch catheters 5 are provided with inner inclined surfaces 8 that are opposite to the outer inclined surfaces 7 and have the same inclination. The distance between the inclined ports of the inner inclined surfaces 8 and the outer inclined surfaces 7 and the outermost annular groove 31 of the branch catheter 5 is 0.5 mm. This setting makes the inlet end face of the branch catheter 5 thinner, and the inclined surface setting makes it easier for the branch catheter 5 to pass through the blood vessel and makes it easier for its tip to pass through the vascular lesion.

[0035] The propulsion component 3 is equidistantly arranged on the surface of the main tube 11 and the two branch catheters 5, such as one every 10 mm. The annular groove 31 at the farthest end of the main tube 11 and / or the two branch catheters 5 corresponds as closely as possible to the distal end of the vascular lesion. The length of the lesion can be roughly determined by X-ray irradiation based on how many annular grooves 31 cover the lesion. At the same time, only one point at the distal end of the lesion needs to be remembered under X-ray irradiation. The distance between the outermost propulsion component 3 of the branch catheter 5 and the marked point is observed based on the length of the retraction of the parallel catheter. In other words, the distance between the outermost propulsion component 3 of the branch catheter 5 and the proximal end of the vascular lesion is observed, so that the vascular lesion is exposed. The balloon drives the stent beam to advance the same distance as the retraction distance of the parallel catheter surface from the lesion, so that the stent beam is located at the vascular lesion. That is to say, the movement distance of the balloon is calculated based on the point corresponding to the proximal end of the vascular lesion of the outermost propulsion component 3 of the branch catheter 5.

[0036] Furthermore, the main pipe 11 has a flow guide shroud 4 integrally formed at one end of each of the two branch pipes 5, and the flow guide shroud 4 is integrally formed at one end of each of the two branch pipes 5.

[0037] It should be noted that the material of this device, except for the silicone ring 32, is the same as that of the existing parallel conduit, and will not be described in detail. Other connecting devices such as push rods and handles are not the main technologies and will not be described in detail.

[0038] The position of the flow shield 4 between the two branch catheters 5 is set as an arc-shaped protrusion, or it can be set as an inward arc-shaped groove. Regardless of the setting, the connection between it and the surface of the two branch catheters 5 is set as a smooth transition, so as to avoid damage to the blood vessel crossing. The flow shield 4 is conical in shape.

[0039] The thickness of the silicone ring 32 is 0.05mm. The thickness should not be too high, otherwise it will affect the structural strength of the two branch catheters 5 and the main catheter 11. At the same time, the silicone ring 32 itself also has strength and can increase the overall strength of the microcatheter 1. The silicone ring 32 is preferably medical sterile silicone. Its material is different from that of the parallel catheters under X-ray, so it is easy to identify and calculate the length.

[0040] The principle and process of this utility model:

[0041] When using this device, the microcatheter 1 is moved to the location of the vascular lesion by the guidewire, and the two branch catheters 5 are inserted into the bifurcated blood vessels. The inclined surfaces of the two branch catheters 5 facilitate the passage of the tip of the microcatheter 1 through the vascular lesion area. At the same time, this device can initially expand the vascular lesion area to increase blood flow. The large arc convex ring 2 and the small arc convex ring 6 can expand their respective blood vessels. The larger diameter results in better expansion effect, making the expansion position wider and facilitating the subsequent placement of the stent beam. At the same time, the better fit with the blood vessel will cause the blood vessel to expand slightly. Even if the user does not operate the microcatheter 1, the microcatheter 1 will not move under the reaction force of the blood vessel. It should be noted that the silicone ring 32 in the annular groove 31 at the front end of the branch catheter 5 or the main tube 11 corresponds to the front end of the lesion. Then, the length of the lesion is calculated by covering the lesion with several silicone rings 32 of the advancement component 3. The length can also be calculated by X-ray irradiation. The redundant design provides higher accuracy.

[0042] After dilation, the user needs to transport the stent beam to the lesion site using a balloon. At this time, the front end of the stent beam corresponds to the silicone ring 32 at the front end of the branch catheter 5 or the main tube 11. Then, the user retracts the microcatheter 1 a certain distance to completely separate the stent beam from the microcatheter 1. It should be noted that the balloon must not be moved during this process, otherwise it will shift and cause the stent beam to be installed in an incorrect position. At this time, the balloon is inflated to open the stent beam and fit it against the blood vessel wall. At this time, the inner diameter of the blood vessel must be larger than the outer diameter of the large arc convex ring 2 and the small arc convex ring 6. It should not be too large to ensure that the blood vessel is not damaged.

[0043] The user can insert one end of the stent beam of the microcatheter 1 into the annular groove 31. Because the surface of the branch catheter 5 between the annular groove 31 and the small arc convex ring 6 is inclined, the annular groove 31 appears to be convex, which makes it easier to insert one end of the stent beam into the annular groove 31. Because the diameter of the stent beam is small and the arc convex ring 6 is large, only one side of the stent beam can be pushed for fine adjustment, so that the stent beam can be further adjusted to the appropriate position at the vascular lesion site, and thus the operation can be repeated.

[0044] In summary, this device can securely fix the catheter within the blood vessel without causing it to move, while the design on the catheter surface allows for fine-tuning of the stent.

[0045] It should be noted that, in this document, relational terms such as "first" and "second" are used only to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such process, method, article, or apparatus.

[0046] Although embodiments of the present invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the present invention, the scope of which is defined by the appended claims and their equivalents.

Claims

1. An optimized catheter placement method for post-procedure stent graft placement in coronary artery bifurcation lesions, characterized in that: It includes a microcatheter (1), which includes a main tube (11) and two branch tubes (5). One end of each branch tube (5) is connected to and fixed at one end of the main tube (11), and a gap is provided between the two branch tubes (5). The surfaces of the main tube (11) and the two branch tubes (5) are all provided with propulsion components (3); The surface of the main tube (11) is provided with a large arc convex ring (2) on one side of the branch tube (5), and the two branch tubes (5) are provided with small arc convex rings (6) on the side away from the main tube (11).

2. The optimized coronary artery bifurcation lesion stent graft placement catheter according to claim 1, characterized in that: The propulsion assembly (3) on the surface of the main tube (11) and the two branch tubes (5) has the same structure but different size. The propulsion assembly (3) includes annular grooves (31) opened on the surface of the main tube (11) and the two branch tubes (5). The outer edge of the annular groove (31) is provided with an arc-shaped chamfer.

3. The optimized coronary artery bifurcation lesion stent graft placement catheter according to claim 2, characterized in that: The main tube (11) and the two branch tubes (5) are embedded with silicone rings (32) located at the bottom of the inner cavity of the annular groove (31), and the outer side of the silicone rings (32) is flush with the bottom of the inner cavity of the annular groove (31).

4. The optimized coronary artery bifurcation lesion stent graft placement catheter according to claim 1, characterized in that: The main tube (11) is integrally formed with the large arc convex ring (2), and the branch tube (5) is integrally formed with the small arc convex ring (6), with the small arc convex rings (6) on the surfaces of the two branch tubes (5) corresponding to each other.

5. The optimized coronary artery bifurcation lesion stent graft placement catheter according to claim 1, characterized in that: The large circular arc protrusion (2) and the small circular arc protrusion (6) protrude from the surfaces of the main tube (11) and the two branch tubes (5), respectively.

6. The optimized coronary artery bifurcation lesion stent graft placement catheter according to claim 1, characterized in that: The openings of the two branch tubes (5) are provided with an outer inclined surface (7) on the side near the outermost propulsion component (3) that is inclined toward the center of the branch tube (5), and the inner walls of the openings of the two branch tubes (5) are provided with inner inclined surfaces (8) that are opposite to the outer inclined surfaces (7) and have the same slope.

7. The optimized coronary artery bifurcation lesion stent graft placement catheter according to claim 1, characterized in that: The main tube (11) is integrally formed with a flow guide (4) at one end of the two branch tubes (5). The two branch tubes (5) are integrally formed with the flow guide (4). The flow guide (4) is located between the two branch tubes (5) and is set in an arc shape to avoid damage to the blood vessel crossing. The flow guide (4) is conical in shape.

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