A comprehensive new abdominal aortic aneurysm endovascular repair stent system

Abstract

The application provides a comprehensive new abdominal aortic aneurysm endoluminal repair stent system, which comprises an aortic covered stent section, a proximal bare stent, a first covered stent section and a second covered stent section, the proximal bare stent is provided with an anchoring barb, the proximal bare stent is connected with the proximal end of the aortic covered stent section, and a support wave is arranged on the outer periphery of the connection part; the first covered stent section is connected with the distal end of the aortic covered stent section; the second covered stent section is connected with the distal end of the aortic covered stent section, the length of the second covered stent section is shorter than that of the first covered stent section, the distal end opening of the second covered stent section has a double curvature arc shape and a height difference in the circumferential direction, a plurality of second developing marks are arranged on the distal end opening of the second covered stent section, and the plurality of second developing marks are arranged at intervals along the circumferential edge of the distal end opening of the second covered stent section, so that the guide wire can be superselected.

Description

Technical Field

[0001] This invention relates to the field of covered stents, and more particularly to a comprehensive novel endovascular repair stent system for abdominal aortic aneurysms. Background Technology

[0002] Endovascular aneurysm repair (EVAR) has become the preferred treatment for subrenal abdominal aortic aneurysms due to its advantages such as being minimally invasive, allowing for rapid recovery, and resulting in low perioperative mortality. This technique involves delivering a endovascular stent graft system to the aneurysm site via femoral artery puncture. After release, the stent graft anchors to the normal vessel wall proximal and distal to the aneurysm neck, thereby isolating the aneurysm cavity from blood flow.

[0003] Currently, commercially available abdominal aortic stent graft systems typically employ a bifurcated design, with the main body branching into two branches distally. During implantation, the main body is fixed to the abdominal aorta below the kidney, with the longer branch extending directly to the iliac artery on the same side as the surgical approach; while the shorter branch is suspended at the aortic bifurcation, serving as an interface connecting to blood flow on the opposite side.

[0004] After the main stent is deployed, the operator must establish an access through the contralateral femoral artery, manipulating the guidewire and catheter system to travel retrogradely upwards and turn at the aortic bifurcation, ultimately superselectively entering the shorter branch suspended there. However, the existing shorter branch usually has a simple round or oval opening. When the patient's aortic bifurcation angle is too small, the iliac artery is severely tortuous, or the abdominal aortic aneurysm is large and irregular in shape, the anatomical space of the aortic bifurcation area becomes exceptionally complex. In such cases, it is difficult for the guidewire tip to achieve stable alignment and capture with the shorter branch, making the superselection process extremely difficult, time-consuming, and heavily dependent on the operator's personal experience and skills. This not only significantly prolongs the operation time but may even lead to superselection failure, thus affecting the success rate of the operation. Summary of the Invention

[0005] The purpose of this invention is to address the shortcomings of existing technologies by providing a comprehensive and novel endovascular stent system for abdominal aortic aneurysm repair.

[0006] To achieve the above objectives, the present invention provides the following technical solution: A novel comprehensive endovascular stent system for repairing abdominal aortic aneurysms, comprising: Aortic endovascular segment; A proximal bare stent, wherein the proximal bare stent is provided with anchoring barbs, the proximal bare stent is connected to the proximal end of the aortic graft segment, and a support wave is provided on the periphery of the connection between the two; The first covered segment is connected to the distal end of the aortic covered segment; The second covered segment is connected to the distal end of the aortic covered segment. The length of the second covered segment is shorter than the length of the first covered segment. The outline of the distal opening of the second covered segment is a hyperbolic arc shape with a height difference in the circumferential direction. The distal opening of the second covered segment is provided with multiple sets of second imaging marks, which are spaced apart along the periphery of the distal opening of the second covered segment.

[0007] In a preferred embodiment, the supporting wave is projected axially as a wave-shaped curve with continuously varying curvature.

[0008] In a preferred embodiment, the supporting wave surface is provided with a porous oxide layer.

[0009] In a preferred embodiment, the proximal bare stent is wavy, with the troughs of the wavy shape connected to the support wave and the crests of the wavy shape connected to the anchoring barbs.

[0010] In a preferred embodiment, the inner surfaces of the first and second coated sections are covered with a continuous inner liner made of expanded polytetrafluoroethylene material, and the surface of the continuous inner liner has a heparinized coating.

[0011] In a preferred embodiment, the outer surface of the aortic endovascular segment is provided with multiple segments of thrombolytic cilia.

[0012] In a preferred embodiment, the distribution density of the thrombolytic cilia gradually decreases from the proximal end to the distal end along the axial direction of the aortic endovascular segment.

[0013] In a preferred embodiment, the thrombotic cilia include radially extending cilia and tangential cilia at an angle of 15-30° to the blood flow direction.

[0014] In a preferred embodiment, the periphery of the distal opening of the second coating segment is provided with at least two second development marks of different shapes or positions.

[0015] In a preferred embodiment, a third contrast marker is provided at the proximal end of the aortic endovascular segment; The distal end of the first coated section is provided with a first developing mark.

[0016] Compared with existing technologies, this technical solution has the following advantages: The distal opening of the second covered segment has a hyperbolic arc shape and a height difference in the circumferential direction. The distal opening of the second covered segment is provided with multiple sets of second imaging markers, which facilitates guidewire superselection, significantly shortens the superselection operation time, reduces the risk of vascular damage caused by repeated attempts, and ultimately improves the overall success rate and safety of the operation.

[0017] The integrated support wave of this invention solves the problem of poor proximal apposition of existing stents under complex aneurysm neck conditions. Through multiple mechanisms such as increasing the apposition area, homogenizing the support stress, and reducing local peak pressure, it provides a fundamental structural solution for preventing type Ia endoleak. At the same time, its biocompatible surface treatment helps to achieve long-term stable treatment results.

[0018] This invention creates an optimized prothrombotic microenvironment within the aneurysm cavity through a multi-dimensional synergistic design incorporating density gradients, length gradients, three-dimensional bifurcation structures, spiral arrangements, and directional functional zoning. This not only significantly improves the efficiency and speed of thrombus formation and actively blocks collateral reflux, but also achieves safe and controllable blood flow blockage through gradient design. This fundamentally reduces the risk of aneurysm enlargement and long-term type II endoleak due to continuous aneurysm cavity perfusion, providing an innovative proactive solution for the long-term stable closure of the aneurysm cavity after EVAR surgery.

[0019] This invention, through the design of an inner liner and a heparinized coating, constructs a blood contact interface that combines excellent blood compatibility, strong active anticoagulation capability, and long-term stability. This design systematically solves the problem of long-term patency of the iliac branch, significantly reducing the risk of iliac branch occlusion after EVAR through multiple mechanisms, including reducing intimal hyperplasia, inhibiting platelet adhesion and aggregation, synergistic anticoagulation, and optimizing local blood flow. Attached Figure Description

[0020] Figure 1 This is a schematic diagram of the structure of the comprehensive novel abdominal aortic aneurysm endovascular repair stent system described in this invention.

[0021] In the figure: 100 aortic endovascular segment, 200 proximal bare stent, 210 anchoring barb, 300 first endovascular segment, 400 second endovascular segment, 500 support wave, 600 thrombotic cilia, 710 first contrast marker, 720 second contrast marker, 730 third contrast marker. Detailed Implementation

[0022] The following description is intended to disclose the present invention and enable those skilled in the art to implement it. The preferred embodiments described below are merely examples, and other obvious variations will occur to those skilled in the art. The basic principles of the invention defined in the following description can be applied to other embodiments, modifications, improvements, equivalents, and other technical solutions that do not depart from the spirit and scope of the invention.

[0023] Please refer to Figure 1 Embodiments of the present invention provide a comprehensive novel endovascular repair stent system for abdominal aortic aneurysms, comprising: 100 mm of aortic endovascular graft; A proximal bare stent 200 is provided with anchoring barbs 210. The proximal bare stent 200 is connected to the proximal end of the aortic graft segment 100, and a support wave 500 is provided on the periphery of the connection between the two. The first covered segment 300 is connected to the distal end of the aortic covered segment 100; The second covered segment 400 is connected to the distal end of the aortic covered segment 100, and the length of the second covered segment 400 is shorter than the length of the first covered segment 300.

[0024] During implantation, the aortic endovascular segment 100 is fixed to the abdominal aorta below the kidney, the longer first endovascular segment 300 extends to the ipsilateral iliac artery, and the shorter second endovascular segment 400 is suspended at the aortic bifurcation, serving as an interface for blood flow reconstruction of the contralateral iliac artery.

[0025] The distal opening of the second coating segment 400 has a hyperbolic arc shape. This opening is not a traditional simple circle or near-circular shape, but rather has a continuously varying height difference along its circumference. This increases the effective projected area and spatial volume of the opening, providing a larger target area for the guidewire tip and reducing the difficulty of aiming.

[0026] At the circumferential location of the distal opening of the second covered segment 400, at least two sets of second contrast markers 720 made of high atomic number materials (such as tantalum-platinum composites) are provided. These markers are not uniformly distributed, but strategically placed at different orientations with height differences (e.g., corresponding to the highest point, lowest point, and lateral turning point) according to the three-dimensional configuration of the opening. Under X-ray fluoroscopy, these high-contrast contrast markers can be clearly displayed, allowing the surgeon to quickly and intuitively determine the precise orientation, rotation, and anterior-posterior position of the opening in three-dimensional space without relying on complex angle projections or repeated angiography. The surgeon can directly adjust the direction of the guidewire based on the relative positional relationship of the marker points to achieve precise alignment. This significantly shortens the superselective procedure time, reduces the risk of vascular injury due to repeated attempts, and ultimately improves the overall success rate and safety of the procedure.

[0027] like Figure 1 As shown, the proximal bare stent 200 is a tubular structure without a membrane covering, which is integrally formed by laser cutting using a medical-grade nickel-titanium alloy with superelasticity and shape memory effect. This proximal bare stent 200 can be composed of a single-layer corrugated ring.

[0028] The aortic graft segment 100 consists of a graft (e.g., polyester fiber PET or expanded polytetrafluoroethylene) and an internally supporting graft stent; the graft stent is typically composed of multiple layers of axially spaced corrugated rings. The troughs of the corrugated rings of the proximal bare stent 200 and the peaks of the corrugated rings closest to the proximal end of the aortic graft segment 100 are formed by methods such as laser welding, suturing, or isovolumetric cutting.

[0029] like Figure 1 As shown, the proximal bare stent 200 also has multiple (e.g., four, evenly distributed circumferentially) radially outwardly extending anchoring barbs 210 on its crest. The anchoring barbs 210 are arc-shaped. The anchoring barbs 210 are preferably made of nickel-titanium alloy and are fixed to the crest by means of laser welding or other methods, for embedding into the blood vessel wall after release to provide axial anchoring force against displacement.

[0030] The proximal bare stent 200 conforms to the vessel wall of the infernal aortic aneurysm neck and provides flexibility; the arc-shaped anchoring barbs 210 actively embed and provide strong axial anti-displacement capability. The two work together to ensure the long-term stability of the stent system under complex hemodynamic environments.

[0031] like Figure 1 As shown, in order to further enhance the wall apposition of the proximal stent system and fundamentally prevent type I endoleak (especially type Ia endoleak) caused by poor apposition between the proximal stent and the arterial wall, the present invention provides an integrally formed support wave 500 on the outer periphery of the connection between the proximal bare stent 200 and the aortic endovascular graft 100.

[0032] The support wave 500 is preferably made of the same medical-grade nickel-titanium alloy as the proximal bare stent 200, and is fixed by laser cutting and forming an integral part of the proximal waveform ring of the aortic graft segment 100. This integrated design ensures the integrity of the structure and the efficiency of mechanical transmission.

[0033] The support wave 500 is a closed-loop annular structure integrally formed with the proximal bare support 200. In the axial projection view, the profile of the support wave 500 appears as a wave-shaped curve with continuously changing curvature and a smooth transition. This profile differs from a simple uniform radius circular arc or a standard sine wave; it can be specifically achieved through an involute-parabolic composite waveform topology. In this configuration, the involute portion provides a gradual change in curvature, which is beneficial for initial low-stress fit; the parabolic portion provides optimized mechanical load-bearing capacity and force flow distribution, and the two are smoothly connected to form a whole. This specific configuration brings significant mechanical advantages: Compared to traditional constant-curvature circular arc waveforms, this waveform with continuously varying curvature can more evenly distribute the radial support force transmitted from the proximal bare support 200. It effectively avoids the concentration of support force at a few peak points, instead distributing the support force across a wider contact surface.

[0034] By providing a smooth, progressive support profile, the support wave 500 facilitates more complete adhesion of the proximal overlay of the aortic overlay segment 100 to the aneurysm neck vessel wall, especially in complex anatomical areas with angulation, calcification, or irregular shapes, significantly increasing the effective sealing area. This ensures tight adhesion while avoiding potential vessel wall damage or long-term complications caused by excessive local pressure.

[0035] To enhance long-term biocompatibility and promote rapid endothelialization, the surface of the support wave 500 can be functionalized. As a preferred embodiment, a porous oxide layer with a thickness of approximately 5-8 μm can be generated on its surface using micro-arc oxidation (MAO) technology. This oxide layer has a porosity of approximately 65% ​​± 5% and a pore size of 20-50 nm. This micro-nano porous structure significantly increases the specific surface area, providing an ideal microenvironment for endothelial cell adhesion, migration, and the formation of a functional endothelial layer, thereby accelerating the biofusion of the stent surface with its own vascular wall and further consolidating the long-term sealing effect.

[0036] like Figure 1 As shown, to address the lack of proactive prevention capabilities of existing stents for type II endoleaks (originating from reflux in collateral vessels such as the inferior mesenteric artery and lumbar artery), this invention incorporates multiple distributed thrombolytic cilia 600 on the outer surface of the aortic endovascular graft 100. This design aims to proactively intervene in the hemodynamics within the aneurysm cavity through a biomimetic structure, inducing thrombosis within the cavity, thereby preventing or treating type II endoleaks at their source.

[0037] The thrombolytic ciliary system of this invention is not uniformly distributed, but rather designed with gradients and functional zones based on the hemodynamic characteristics within the aneurysm cavity. Its core lies in constructing a transitional environment from high to low blockage along the stent axis (i.e., the direction of blood flow), achieving a synergistic effect of rapid proximal occlusion, mid-segment deceleration guidance, and balanced distal drainage. This efficiently promotes thrombus formation while avoiding compensatory collateral dilation caused by excessive embolism.

[0038] Specifically, the distribution density of the thrombolytic cilia 600 decreases gradually from proximal to distal along the axial direction of the aortic endovascular segment 100. It can be divided into three functional zones: Proximal high-density thromboproliferative zone: Located in the proximal 1 / 3 of the aortic endovascular segment 100, this area has the highest ciliary density (e.g., approximately 120 cilia / mm²) and the smallest spacing (e.g., approximately 80 μm). This area forms a dense primary fibrous network that rapidly captures blood components, inducing the formation of a stable initial thrombus barrier that directly blocks the impact of the main reflux flow.

[0039] Mid-segment transition deceleration zone: Located in the middle third of the aortic endovascular segment 100, this area has moderate ciliary density (e.g., approximately 60 cilia / mm²) and increased spacing (e.g., approximately 150 μm). This area guides blood flow stratification and deceleration, prolongs the contact time between blood and cilia, and promotes thrombus expansion and consolidation.

[0040] Distal low-density drainage balance zone: Located in the approximately 1 / 3 region distal to the 100mm distal end of the aortic endovascular graft, this zone has the lowest ciliary density (e.g., approximately 20 cilia / mm²) and the largest spacing (e.g., approximately 300μm). This zone allows a small amount of blood flow to pass slowly, preventing a sudden increase in pressure due to complete occlusion of the aneurysm cavity, which could then trigger open reflux in other collateral vessels or pressure imbalance within the aneurysm.

[0041] Each individual ciliary adopts a conical, three-tiered branching structure, with its tip resembling a nanosphere. This design significantly increases the surface area of ​​each ciliary compared to traditional straight fibers, providing a richer pool of sites for platelet adhesion, aggregation, and activation of the coagulation cascade.

[0042] The length of the cilia also varies from proximal to distal (for example, the proximal length is about 3.0 mm and the distal length is about 1.5 mm), which, together with the density gradient, forms a three-dimensional blood flow blocking network with spatial depth.

[0043] The cilia are not arranged vertically, but rather around the surface of the aortic endovascular segment 100 at a spiral angle of approximately 45° (pitch approximately 1.2 mm). This spiral arrangement makes it easier for them to form orthogonal interleavings with the shear direction of the complex, multidirectional eddies or slow-flowing blood within the aneurysm cavity, greatly improving the efficiency of the interaction between the cilia and the blood flow.

[0044] The ciliary community consists of two types of cilia with different functional orientations: radial cilia (about 40%) are perpendicular to the blood flow direction and mainly play a role in directly intercepting blood cells; tangential cilia (about 60%) are at an angle of about 15-30° to the blood flow direction and their main function is to induce controllable microvortices, significantly prolong the retention time of blood in the tumor cavity, and create a more favorable static or low-shear environment for thrombosis.

[0045] The thromboproliferative cilia 600 are preferably made of medical-grade polyester fiber with good biocompatibility and stable mechanical properties. They possess excellent flexibility and foldability, ensuring that the system's permeability is not affected during stent delivery, and that they can fully unfold after deployment, maintaining structural integrity and thromboproliferative activity over the long term.

[0046] like Figure 1 As shown, the inner surfaces of the first coated section 300 and the second coated section 400 are covered with a continuous inner liner made of expanded polytetrafluoroethylene material, and the surface of the continuous inner liner has a heparinized coating.

[0047] Expanded polytetrafluoroethylene (ePTFE) is a mature biomaterial widely used in artificial blood vessels and stent structures. Its excellent biocompatibility and low-friction properties significantly reduce the risk of thrombosis. The material's flexibility and torsion resistance ensure the stent maintains its shape stability during delivery and deployment, while also providing a degree of safety and durability. Combined with a heparinized coating design, it reduces blood-blood interactions, exerts an antithrombotic effect, further enhances the anticoagulant properties of the stent's inner surface, reduces platelet adhesion and coagulation factor activation, and the optimized leg length design helps reduce blood flow turbulence at iliac artery branches.

[0048] Argon-oxygen mixed plasma treatment is applied to the surface of expanded polytetrafluoroethylene material to form a nanoscale rough structure, which enables the heparin coating to be fixed by covalent grafting, thereby improving the coating retention rate and prolonging the dynamic clotting time.

[0049] In a preferred embodiment, the heparinized coating is a heparin-nitric oxide bifunctional coating. Layer-by-layer self-assembly (LBL) technology is used to alternately and precisely deposit heparin and nitric oxide donors (such as diazenium diolate compounds) onto the substrate. Incorporating nanodiamonds into the inner liner reduces the coating peeling area to <0.5% and lowers the coefficient of friction. By combining the anatomical characteristics of the patient's CTA images, accurate iliac artery anatomical parameters are obtained, allowing for customized optimization of the angle and length of the long and short legs to minimize blood flow disturbance.

[0050] like Figure 1 As shown, a third contrast marker 730 is provided at the proximal edge of the aortic graft segment 100. This marker is positioned closer to the proximal end of the stent than the support wave 500. Under X-ray fluoroscopy, the third contrast marker 730, combined with the image of the support wave 500, enables precise release of the proximal anchoring zone. The first contrast marker 710 is observed to confirm the length and position of the first graft segment 300.

[0051] The method of using the comprehensive new abdominal aortic aneurysm endovascular repair stent system is as follows: Step 1: Introduction of the conveyor system and preliminary positioning at the near end A primary delivery pathway is established by percutaneous puncture of one (e.g., the right) femoral artery. Under the guidance of an ultra-stiff guidewire, the delivery system containing the stent of this invention is advanced through the aorta to the predetermined treatment area of ​​the infrarenal abdominal aortic aneurysm.

[0052] Under X-ray fluoroscopy, the delivery system is adjusted so that the third contrast marker 730 at the proximal end of the stent is precisely aligned with the distal end of the healthy aneurysm neck at the lower margin of the renal artery orifice. Simultaneously, the contrast profiles of the proximal bare stent 200 and the support wave 500 are observed to ensure they are completely within the predetermined anchoring area.

[0053] Step 2: Release of the main body and orientation of the opposite interface The inner core of the fixed delivery system is slowly retracted, partially releasing the stent body. During this process, the proximal bare stent 200 and its anchoring barbs 210 first deploy and anchor to the aneurysm neck, followed by the deployment of the aortic graft segment 100.

[0054] Continue withdrawing the outer sheath until the second covered segment 400 of the stent (contralateral interface) is fully opened and suspended at the aortic bifurcation. At this point, multiple sets of second contrast markers 720 around the distal opening can be clearly observed under fluoroscopy. Based on the specific relative positional relationship of these markers on the two-dimensional image, the surgeon can immediately and intuitively determine the precise orientation of the hyperbolic arc-shaped opening with height difference in three-dimensional space.

[0055] Step 3: Establishment and bridging of the contralateral iliac artery access. A catheter and guidewire system is introduced via puncture of the contralateral (left) femoral artery. Under fluoroscopic guidance, the guidewire tip is advanced to the aortic bifurcation.

[0056] Using the distal opening of the second coated section 400, whose direction was determined in step two, as a guiding target point, the guidewire is manipulated. Thanks to the arc-shaped guide surface and height difference design of this opening, the tip of the guidewire is easily captured and smoothly guided into the opening, thereby completing the crucial step of superselection of the second coated section 400.

[0057] After replacing the guidewire with an ultra-stiff one and establishing a stable track, a suitable-length independent iliac branch covered stent is advanced along this track. Its proximal end is fully overlapped with the distal opening of the second covered segment 400 and released, with the distal end anchored to a healthy segment of the left iliac artery, thus completing contralateral blood flow reconstruction.

[0058] Step 4: Completion and final release of the ipsilateral blood flow channel Return to the main delivery system side (right side). After confirming that the contralateral bridging is complete and the stent position is satisfactory, fully release the delivery system so that the first covered segment 300 is fully deployed, and its distal first imaging marker 710 should be located in the target area of ​​the ipsilateral (right) iliac artery.

[0059] Based on preoperative assessment or intraoperative measurements, if the ipsilateral branch length is insufficient or needs to be extended further, another iliac branch stent can be inserted through the ipsilateral access, so that its proximal end fully overlaps with the distal end of the first covered segment 300 (with the first imaging marker 710 as a reference), and the distal end is anchored in an appropriate position.

[0060] Step 5: Post-balloon dilation and final shaping Using a compliant balloon catheter, low-pressure post-dilation is performed sequentially on the following key areas. For example, dilation is performed on the aneurysm neck region where the proximal bare stent 200 and wave 500 are located to optimize apposition and maximize sealing by utilizing the uniform stress distribution characteristics of the supporting wave 500 to prevent type Ia endoleak.

[0061] After implantation, the stent system of this invention effectively isolates the aneurysm cavity through the proximal composite anchoring sealing unit (bare stent, barbs, and support wave) to prevent type Ia endoleak; actively induces thrombosis of the aneurysm cavity through surface thrombolytic cilia 600 to prevent type II endoleak; maintains branch patency through the inner liner and heparinized coating; and its unique guiding opening and imaging system ensure the precision and efficiency of the surgical procedure.

[0062] The embodiments described above are only used to illustrate the technical ideas and features of the present invention. Their purpose is to enable those skilled in the art to understand the content of the present invention and implement it accordingly. The scope of patent application of the present invention should not be limited by these embodiments. That is, any equivalent changes or modifications made in accordance with the spirit disclosed in the present invention still fall within the patent scope of the present invention.

Claims

1. A novel comprehensive endovascular stent system for repairing abdominal aortic aneurysms, characterized in that, include: Aortic laparotomy segment (100); A proximal bare stent (200) is provided with anchoring barbs (210), the proximal bare stent (200) is connected to the proximal end of the aortic graft segment (100), and a support wave (500) is provided on the periphery of the connection between the two. The first covered segment (300) is connected to the distal end of the aortic covered segment (100) for extending into the ipsilateral iliac artery; The second covered segment (400) is connected to the distal end of the aortic covered segment (100). The length of the second covered segment (400) is shorter than that of the first covered segment (300). When implanted, it is suspended at the aortic bifurcation as an interface for blood flow reconstruction of the contralateral iliac artery. The outline of the distal opening of the second covered segment (400) is a hyperbolic arc with a height difference in the circumferential direction. The distal opening of the second covered segment (400) is provided with multiple sets of second imaging markers (720). The multiple sets of second imaging markers (720) are spaced along the periphery of the distal opening of the second covered segment (400). At least two second imaging markers (720) have different shapes or circumferential positions, which increases the effective projection area of ​​the distal opening and expands the guidewire superselective target area under X-ray fluoroscopy.

2. The comprehensive novel endovascular repair stent system for abdominal aortic aneurysms as described in claim 1, characterized in that, The support wave (500) is projected axially as a wave-shaped curve with continuously changing curvature.

3. The comprehensive novel endovascular repair stent system for abdominal aortic aneurysms as described in claim 1, characterized in that, The surface of the support wave (500) is provided with a porous oxide layer.

4. The comprehensive novel endovascular repair stent system for abdominal aortic aneurysms as described in claim 1, characterized in that, The proximal bare support (200) is wavy, with the troughs of the wave connected to the support wave (500) and the crests of the wave connected to the anchor barbs (210).

5. The comprehensive novel endovascular repair stent system for abdominal aortic aneurysms as described in claim 1, characterized in that, The inner surfaces of the first coated section (300) and the second coated section (400) are covered with a continuous inner liner made of expanded polytetrafluoroethylene material, and the surface of the continuous inner liner has a heparinized coating.

6. The comprehensive novel endovascular repair stent system for abdominal aortic aneurysms as described in claim 1, characterized in that, The outer surface of the aortic endovascular segment (100) is provided with multiple segments of thrombolytic cilia (600).

7. The comprehensive novel endovascular repair stent system for abdominal aortic aneurysms as described in claim 6, characterized in that, Along the axial direction of the aortic endothelial segment (100), the distribution density of the thrombotic cilia (600) gradually decreases from the proximal end to the distal end.

8. The comprehensive novel endovascular repair stent system for abdominal aortic aneurysms as described in claim 6, characterized in that, The thrombotic cilia (600) include radially extending cilia and tangential cilia at an angle of 15-30° to the direction of blood flow.

9. The comprehensive novel endovascular repair stent system for abdominal aortic aneurysms as described in claim 1, characterized in that, The periphery of the distal opening of the second coating segment (400) is provided with at least two second development marks (720) of different shapes or positions.

10. The comprehensive novel endovascular repair stent system for abdominal aortic aneurysms as described in claim 1, characterized in that, The proximal end of the aortic endovascular segment (100) is provided with a third contrast marker (730). The distal end of the first coated section (300) is provided with a first developing mark (710).

Images