Rapid exchange stent delivery system

Abstract

This invention discloses a rapid stent delivery system, comprising an outer tube assembly, an inner tube assembly, a stent, and a dual-lumen connector. The outer tube assembly has an inner lumen for accommodating the inner tube assembly and providing space for stent loading; the outer tube assembly is slidable. The inner tube assembly is disposed within the inner lumen of the outer tube assembly. The stent is loaded onto the outer side of the inner tube assembly. The dual-lumen connector is disposed on the outer tube assembly, and has a first lumen and a second lumen inside. The first lumen has a guiding structure to allow the guidewire to slide smoothly from a side outlet; the second lumen is used for the sliding of the inner tube assembly, providing sliding guidance and limiting functions. This invention, through optimized guidewire guiding structure and limiting design of the inner and outer tubes, achieves smooth guidewire path guidance and stent release, with stable and precise operation, and is particularly suitable for stent delivery and release procedures in complex cavities.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to a rapid exchange stent delivery system suitable for medical procedures involving stent delivery and release. Background Technology

[0002] Rapid-change stent delivery systems are widely used in endoscopic stent delivery and deployment procedures, particularly suitable for surgeries involving complex cavities, tortuous pathways, or narrow anatomical structures. These systems typically consist of an outer cannula assembly, an inner cannula assembly, and a guidewire guidance structure, with the guidewire guiding the delivery system to the target location. However, current technologies still have shortcomings in terms of system stability and operational precision.

[0003] For example, US20200352764A1 discloses a rapid exchange conveyor that uses an inclined groove design for guide wire guidance. However, the inclined groove is a thin, sheet-like structure, which is prone to deformation or displacement due to external forces, affecting the guiding accuracy of the guide wire and the stability of the system.

[0004] For example, CN103876873A designs a guide wire guide tube and guide groove for stabilizing the guide wire path. However, this technology lacks effective limiting measures for the inner and outer tubes, which are prone to relative rotation during operation, affecting the stability of the guide wire path and consequently the accuracy of stent release.

[0005] To address the aforementioned technical problems, this invention proposes an improved rapid exchange stent delivery system. By optimizing the guidewire guiding path, the inner and outer tube limiting design, and the structure of the stent release space, the stability of guidewire guidance and the operational accuracy of the system are significantly improved. Summary of the Invention

[0006] The purpose of this invention is to provide a rapid stent delivery system that addresses problems in the prior art, such as unstable guide wire guidance, insufficient control of inner and outer tube rotation, and limited stent release space, thereby improving the system's operational stability and the accuracy of stent delivery and release.

[0007] To achieve the above objectives, the present invention provides a rapid exchange support delivery system, comprising:

[0008] An outer tube assembly has an inner cavity for accommodating an inner tube assembly and providing space for mounting a support; the outer tube assembly is slidable to allow for the release of the support.

[0009] The inner tube assembly is disposed within the inner cavity of the outer tube assembly;

[0010] A bracket is mounted on the outside of the inner tube assembly;

[0011] A dual-cavity connector is provided on the outer tube assembly.

[0012] The dual-cavity connector is an important component of this invention, located in the distal region of the outer tube assembly. The dual-cavity connector includes a first cavity and a second cavity. The first cavity has an inclined guide structure, allowing the guide wire to slide out from the side outlet of the first cavity along the guide structure. The guide structure of the first cavity forms an inclination angle of 5° to 30° relative to the length axis of the first cavity, ensuring smooth sliding of the guide wire through the side outlet. The second cavity slides into the inner tube assembly, and its inner wall cross-sectional shape is consistent with the outer wall cross-sectional shape of the inner tube assembly. A fitting gap is provided between them to ensure smooth sliding and effectively limit the relative rotation of the inner and outer tube assemblies. The cross-sectional shape is a crescent-shaped groove or an arc-shaped groove.

[0013] The inner tube assembly features a groove in its middle section, which slides into the second cavity of the dual-cavity connector. The length of the groove is not less than the length of the support, ensuring stability during release. The groove can be machined using methods such as machining, laser cutting, embossing, or splicing. Furthermore, to enhance the overall system performance, the inner tube assembly is made of PEEK material to improve its high-temperature resistance and high strength. The dual-cavity connector is made of Pebax or PA material, a polymer with low frictional resistance and biocompatibility, and is fixedly connected to the outer tube assembly via thermofusion welding or laser welding, thereby improving connection reliability.

[0014] The outer tube assembly of the present invention is further optimized to consist of a distal outer tube and a proximal outer tube, wherein the outer diameter of the distal outer tube is larger than the outer diameter of the proximal outer tube, so as to meet the requirement of the stent loading area for a larger diameter, while ensuring smooth insertion of the proximal outer tube into the human body cavity.

[0015] Through the above design, the present invention innovates and optimizes in terms of structure and material selection, and has the following beneficial effects compared with the prior art:

[0016] First, the inclined guiding structure of the first cavity significantly reduces the resistance to guidewire slippage, making the guidewire guidance process smoother. Second, the limiting function of the second cavity effectively avoids the relative rotation of the inner and outer tube assemblies during delivery, improving the stability of system operation. Furthermore, the groove design of the inner tube assembly makes stent release smoother and more adaptable. Optimized material selection significantly improves the system's durability and reliability, meeting the needs of complex surgical scenarios. Finally, the use of thermofusion welding or laser welding ensures the robustness between the various components of the system, further enhancing overall performance.

[0017] In summary, this invention provides a stable and structurally optimized rapid exchange stent delivery system, which not only solves many problems in the prior art, but also significantly improves the system's ease of operation and reliability, and has broad clinical application value. Attached Figure Description

[0018] Figure 1 A schematic diagram of the overall structure of the rapid exchange support conveyor system;

[0019] Figure 2 A cross-sectional view of a dual-cavity connector in a rapid exchange support transport system;

[0020] Figure 3 A side view of a dual-cavity connector in a rapid-change support transport system;

[0021] Figure 4A for Figure 2 A schematic diagram of the structure along section AA;

[0022] Figure 4B for Figure 2 A schematic diagram of the structure along the BB section;

[0023] Figure 5 A plan view of the inner tube assembly of a fast-change support conveyor system;

[0024] Figure 6A for Figure 5 A schematic diagram of the structure along section AA;

[0025] Figure 6B for Figure 5 A schematic diagram of the structure along the BB section;

[0026] Figure 6C for Figure 5 A schematic diagram of the structure along the CC section;

[0027] Figure 7 This is a schematic diagram of the guidewire path in a rapid exchange stent delivery system; (showing the process of the guidewire sliding through the first cavity to the outside).

[0028] Figure 8-10 This is a schematic diagram illustrating the dynamic release of the support in a rapid exchange support delivery system; (showing the relative movement of the inner and outer tube assemblies).

[0029] in, Figure 8 This is a cross-sectional view before the stent is deployed;

[0030] in, Figure 9 This is a cross-sectional diagram of the stent deployment process;

[0031] in, Figure 10 This is a cross-sectional view after the stent has been deployed.

[0032] Figure 11 A schematic diagram of the function of the second cavity in a rapid exchange stent delivery catheter system;

[0033] Figure 12A for Figure 11 A schematic diagram of the structure along section AA;

[0034] Figure 12B for Figure 11 A schematic diagram of the structure along the BB section.

[0035] Explanation of reference numerals in the attached figures

[0036] Inner tube assembly 1;

[0037] Inner tube body 11; Slide groove 12; Guide wire inlet 13;

[0038] Outer tube assembly 2;

[0039] Distal outer tube 21; Proximal outer tube 22;

[0040] Dual-cavity connector 3

[0041] First cavity 31; Second cavity 32; Guide ramp 33; Guide wire exit 34;

[0042] Guide wire 4;

[0043] 5. Detailed Implementation

[0044] The directional terms used in this specification (such as "center," "longitudinal," "lateral," "upper," "lower," "front," "rear," etc.) are based solely on the orientation shown in the accompanying drawings and are for ease of description rather than limiting the specific device; they do not specifically refer to the actual orientation of the device. Terms such as "first," "second," etc., are used only to distinguish similar elements and do not represent relative importance. Unless explicitly stated, "upper" or "lower" in the description may refer to direct contact between elements or indirect contact through other structures.

[0045] In the description of this invention, the terms "one embodiment," "some embodiments," etc., mean that the features described in connection with the example are included in at least one embodiment of the invention. Those skilled in the art can combine features of different embodiments as needed to meet specific application requirements.

[0046] Static system structure:

[0047] like Figure 1 As shown, the present invention provides a rapid exchange support delivery system, including an outer tube assembly 2, an inner tube assembly 1, and a dual-cavity connector 3, the structure of each component as described below.

[0048] For ease of explanation, the positional relationships of the system components are defined in this invention as follows: "distal end" refers to the end of the system closest to the patient's target treatment site, typically the area for stent loading, deployment, and guidewire path guidance. For example, the distal outer tube 21 of the outer tube assembly 2 and the dual-lumen connector 3 are both located in the distal region of the system to facilitate contact with the target area and completion of stent deployment during clinical surgery.

[0049] "Proximal end" refers to the end of the system closest to the operator, which is usually the location of the handle part used to control the system. For example, the proximal outer tube 22 of the outer tube assembly 2 is connected to the operating handle, which makes it convenient for doctors to perform operations such as advancing, withdrawing and changing instruments.

[0050] The outer tube assembly 2 is the outer layer of the system, mainly used to support the stent 5 and protect the inner tube assembly 1. The outer tube assembly 2 includes a distal outer tube 21 and a proximal outer tube 22. The distal outer tube 21 is located at the front end of the outer tube assembly 2 and has a larger outer diameter (preferably in the range of 6Fr to 12Fr) to provide sufficient internal space for loading and protecting the stent 5, ensuring that the stent can be stably wrapped and released during delivery. The proximal outer tube 22 is located at the rear end of the outer tube assembly 2 and has a smaller outer diameter (preferably in the range of 4Fr to 8Fr). It is connected to the operating handle for easy operation, adapts to the passage requirements of the endoscope forceps channel and human body cavity, and reserves space for the guide wire 4 to pass through together with the delivery device, ensuring that the guide wire slides out from the lateral outlet 34 of the dual-lumen connector 3 and smoothly enters the endoscope forceps channel.

[0051] The inner tube assembly 1 is coaxially arranged within the inner cavity of the outer tube assembly 2, and remains stationary in its initial state. A sliding groove 12 is provided in the middle section of the inner tube assembly 1, such as... Figure 5 As shown, the cross-section of the groove 12 is a crescent-shaped or arc-shaped groove structure, with its opening facing the inner cavity of the outer tube assembly 2 and extending along the axial direction of the inner tube assembly 1. Figure 6A , 6B As shown in 6C Figure 5 A schematic diagram of the structure along lines AA, BB, and CC. The length of the slide groove 12 matches or is slightly longer than the length of the support 5, ensuring complete release of the support. The slide groove 12 forms a sliding fit with the second cavity 32 of the double-cavity connector 3, ensuring that the outer tube assembly 2 slides smoothly along the slide groove 12 during retraction, limiting radial rotation, and maintaining the coaxial structural stability of the system.

[0052] This invention, through the innovative design of a dual-lumen connector, achieves precise guidance of the guidewire sliding path and efficient limiting of the inner and outer tube components, significantly improving system stability and stent release smoothness in complex surgical scenarios. The shape design and precision machining of the groove further enhance the accuracy of stent positioning, significantly reducing operation time compared to traditional designs, making it particularly suitable for medical environments with narrow cavities.

[0053] like Figure 2 and Figure 3 As shown, the dual-cavity connector 3 is fixedly disposed at the distal end of the outer tube assembly 2. The dual-cavity connector 3 is provided with a first cavity 31 and a second cavity 32. Both the first cavity 31 and the second cavity 32 are formed by the tube wall of the dual-cavity connector, which isolates them from each other and they are not interconnected. The first cavity 31 is used for guide wire guidance, providing a sliding path for the guide wire 4. The guide wire 4 enters from the guide wire inlet 13 of the conveyor (located at the tip of the conveying system), passes through the inner tube body 11 of the inner tube assembly 1, enters the first cavity 31 from the opening side of the chute 12, and smoothly transitions through the guide structure, preferably a ramp guide. In this embodiment, specifically through the inclined guide structure 33, the guide wire can move along the guide structure and slide out from the side outlet 34 of the first cavity 31, leaving the conveyor.

[0054] The structure of the first cavity 31 is as follows: Figure 2 As shown, its initial cross-section is circular or arc-shaped, with a diameter slightly larger than guidewire 4, providing a smooth guidewire passage path and reducing initial sliding resistance. For example... Figure 4A and Figure 4B As shown, Figure 2 The structural schematic diagram of the cross-sections AA and BB shows that the center of the cross-section of the first cavity 31 gradually moves away from the second cavity along the guidewire entry direction. Its transition section is achieved by the guide ramp 33, the surface of which is a smooth arc transition or a multi-segment inclined design. The inclination angle formed by the ramp relative to the length axis of the first cavity 31 is preferably 5° to 30°. This angle range can ensure smooth guidance of the guidewire path.

[0055] The second cavity 32 is located within the double-cavity connector 3, and has a closed annular cross-section. It mates with the outer wall of the inner tube assembly 1 to provide guidance and restrict its relative rotation. Figure 11 The diagram shown is a functional illustration of the second cavity in a rapid stent exchange delivery catheter system. Figure 12A , 12B for Figure 11 The diagram shows the structural structure along cross-sections AA and BB. The second cavity 32 of the double-cavity connector 3 forms a sliding fit with the groove 12 of the inner tube assembly 1, constituting a guide and limiting area between the outer tube assembly 2 and the inner tube assembly 1. This area ensures that the outer tube assembly 2 slides in a controlled manner along the groove 12 during retraction and restricts radial rotation, maintaining the coaxial structure of the system. The fit clearance between the second cavity 32 and the inner tube assembly 1 is preferably 0.05mm to 0.2mm, ensuring smooth sliding while preventing rotational offset during system operation. The cross-sectional shape of the inner wall of the second cavity 32 is consistent with the cross-sectional shape of the outer wall of the inner tube assembly 1, and the cross-sectional shape is a crescent-shaped groove or an arc-shaped groove.

[0056] Through the above structural design, such as Figure 7The diagram shows the guidewire path in the rapid exchange stent delivery system, illustrating the process of the guidewire sliding through the first cavity to the outside. The rapid exchange stent delivery system of this invention achieves precise coordination between the outer tube assembly 2, the inner tube assembly 1, the dual-lumen connector 3, and the slide groove 12. The structural cooperation between the slide groove 12 and the second cavity 32 provides a stable sliding guide function, ensuring the controlled retraction of the outer tube assembly 2 during stent release. The design of the first cavity 31 and the guide ramp 33 provides a smooth sliding path for the guidewire 4, avoiding path jamming or deviation, ensuring the guidewire leaves the delivery system, making it particularly suitable for surgical environments with complex cavities. Furthermore, the length of the slide groove 12 matches the length of the stent 5, ensuring the stent can be released smoothly and efficiently, improving the stent's positioning accuracy and release effect.

[0057] In addition, the dual-cavity connector 3 and the outer tube assembly 2 are connected by laser welding or hot melt welding to improve the connection strength and avoid the risk of breakage, thus ensuring a firm connection.

[0058] In addition, the groove 12 can be processed by laser cutting, embossing or splicing to meet the processing requirements of different structural designs.

[0059] like Figure 1 As shown, the dual-cavity connector 3 is fixedly disposed at the distal end of the outer tube assembly 2, and its position design must ensure that sufficient loading and placement space is provided for the bracket 5. In this invention, the preferred position of the dual-cavity connector 3 is within the range of 100mm to 350mm from the distal end of the device.

[0060] Specifically, the inner cavity of the distal outer tube 21 of the outer tube assembly 2 is used to load the bracket 5. Sufficient space is required for the bracket in the loaded state to ensure it is completely enclosed and protected. For example, in this embodiment, the dual-cavity connector 3 is positioned approximately 150mm from the distal end of the device. With this structure, the system successfully loads a 120mm long bracket, and during bracket release, the retraction of the outer tube assembly 2 is smooth and stable, allowing the bracket to unfold.

[0061] Through the static structural design of the above system, this invention achieves precise coordination and limiting / guiding functions between the various components. The outer tube assembly 2, the inner tube assembly 1, and the double-cavity connector 3 work together to form a stable sliding and limiting structure, laying the foundation for the smooth release of the support and the smooth operation of the system. The following will describe in detail the functional implementation of the system in actual operation, combined with the dynamic usage process.

[0062] Dynamic usage process:

[0063] like Figure 8-10As shown, the rapid exchange stent delivery system of the present invention is divided into four stages during use: guide wire pre-positioning process, delivery system entry process, stent release process, and delivery system withdrawal process.

[0064] During guidewire placement, such as Figure 8 The diagram shown is a cross-sectional view before stent deployment. Guidewire 4 is pre-inserted through the endoscope's channel, extends along the channel to the treatment target location, and is fixed, providing path guidance for the delivery device. At this time, guidewire 4 is in a stationary state, serving as the path reference for system operation.

[0065] During the delivery process, the operator pushes the delivery system using the operating handle. The outer tube assembly 2 and the inner tube assembly 1, as a whole, are gradually moved into the target position along the forceps channel under the guidance of the guidewire 4. The distal outer tube 21 enters the forceps channel first, and the stent loading area moves closer to the target treatment position as the outer tube assembly 2 is advanced, ensuring precise path guidance.

[0066] The guide wire 4 enters from the guide wire inlet 13 of the conveyor, passes through the support loading area of ​​the distal outer tube 21, and enters the first cavity 31 of the dual-cavity connector 3. Through the smooth transition of the guide ramp 33 in the first cavity 31, the guide wire 4 extends from the guide wire outlet 34 on the side.

[0067] During the stent release process, such as Figure 9 The diagram shows a cross-sectional view during the stent release process. The operator gradually retracts the outer tube assembly 2 using the proximal handle, while the inner tube assembly 1 remains stationary. At this time, relative sliding occurs between the outer tube assembly 2 and the inner tube assembly 1, and the slide groove 12 and the second cavity 32 form a stable limiting guide, allowing the outer tube assembly 2 to smoothly retract along the slide groove 12 without radial rotation or path deviation. As the outer tube assembly 2 gradually retracts, the stent 5 encased within the distal outer tube 21 is released and unfolded, and the length of the slide groove 12 matches the length of the stent 5. When the distal outer tube 21 retracts to the proximal boundary point of the slide groove 12, as shown... Figure 10 The diagram shows a cross-sectional view after stent release. Stent 5 is fully released and stably positioned in the target area. Guide wire 4 remains stationary throughout, ensuring a smooth release path and precise stent release direction with controlled positioning.

[0068] During the withdrawal of the delivery system, the stent 5 is fully released and stably positioned within the target cavity, and the delivery system no longer affects the stent. The operator uses the operating handle to synchronously withdraw the outer tube assembly 2 and the inner tube assembly 1 as a whole, and the delivery system gradually withdraws from the endoscope's clamping channel along the guide wire 4 until it is completely withdrawn from the body.

[0069] Throughout the withdrawal process, guidewire 4 remains stationary, serving as a pathway guide and effectively preventing the system from contacting or interfering with the deployed stent, ensuring stent stability. The rapid withdrawal design of the delivery system allows physicians to quickly replace new instruments (such as new delivery systems, stone retrieval baskets, balloon dilation catheters, etc.) using the same guidewire without needing to reinsert the guidewire, significantly shortening surgical time, simplifying procedures, and improving clinical surgical efficiency and safety.

[0070] Therefore, the rapid exchange design of this invention fully utilizes the static characteristics of the guidewire 4 and the side guidewire outlet 34 of the dual-lumen connector 3 to achieve rapid withdrawal of the delivery system and efficient instrument exchange. Unlike traditional delivery systems, the guidewire path of this invention is optimized. The guidewire only needs to pass through the front end area of ​​the delivery system (including the distal outer tube 21 and the first cavity 31 of the dual-lumen connector 3) without penetrating the entire inner cavity of the delivery system, effectively shortening the length of the guidewire within the system. This design significantly reduces frictional resistance and operational complexity in the guidewire path, while optimizing the reserved length of the guidewire at the surgeon's end. Typically, only 1.5-2 meters are needed to complete the operation, making it particularly suitable for surgical environments with limited space or guidewire length. Furthermore, the static characteristics of the guidewire effectively avoid the risk of path deviation or tissue friction damage caused by repeated guidewire movement, ensuring the stability of the guidewire path, thereby improving the overall safety, ease of operation, and efficiency of the surgery.

[0071] In the rapid exchange stent delivery system of the present invention, in order to meet the performance requirements of the system in complex cavity environments, material selection and processing technology optimization were carried out based on the functional characteristics of different components. At the same time, the size matching control between different parts was combined to ensure that the system has high strength, low friction, excellent flexibility and biocompatibility.

[0072] First, in terms of material selection, the dual-cavity connector 3 is made of a polymer material with high strength, good flexibility, low frictional resistance and biocompatibility, preferably Pebax or PA.

[0073] The inner tube assembly 1 is preferably made of high-performance engineering plastic PEEK (polyether ether ketone). PEEK material has high strength, flexibility and high temperature resistance. The wall thickness is controlled between 0.1 mm and 0.3 mm, which not only ensures the operational stability of the inner tube assembly 1, but also can adapt to the bending shape of the cavity, providing support for the operational flexibility of the system.

[0074] In terms of processing technology, to achieve the complex structure and high precision requirements of the dual-cavity connector 3, this invention adopts injection molding, using a multi-cavity mold for precision injection molding to ensure the geometric accuracy and surface smoothness of the first cavity 31 and the second cavity 32. The inner tube assembly 1 is processed by extrusion molding, with the wall thickness accuracy controlled within ±0.02mm, ensuring dimensional accuracy and stability. In addition, the groove 12 in the middle section of the inner tube assembly 1 can be formed by mechanical processing methods such as laser cutting and embossing, or by splicing. Laser cutting is suitable for processing high-precision complex shapes, embossing is used to form grooves by applying mechanical pressure with a mold, and splicing involves joining the semi-circular extruded tube with the circular extruded tubes at both ends to form a complete groove structure.

[0075] In summary, this invention selects materials (such as Pebax, PA, PEEK, etc.) according to the functional requirements of different components, and combines advanced processing technologies such as injection molding, extrusion molding and laser cutting to ensure that each component of the system has excellent dimensional accuracy, strength and flexibility, effectively reduce guidewire sliding resistance, improve the stability and flexibility of the system in complex cavity operations, and meet the high precision and high reliability requirements of clinical surgery.

[0076] The device embodiments described above are merely illustrative. The units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple network units. Some or all of the modules can be selected to achieve the purpose of this embodiment according to actual needs. Those skilled in the art can understand and implement this without any creative effort.

[0077] It is further understood that although the operations are described in a specific order in the accompanying drawings in the embodiments of the present invention, this should not be construed as requiring these operations to be performed in the specific order or serial order shown, or requiring all the operations shown to obtain the desired result. In certain environments, multitasking and parallel processing may be advantageous.

[0078] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, and are not intended to limit them. Although the present invention 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 of the technical features, or different combinations of the above technical features can be made. These modifications, substitutions and combinations do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of the present invention.

Claims

1. A rapid exchange support conveying system, characterized in that, include An outer tube assembly having an inner cavity for accommodating an inner tube assembly and providing space for a support mounting, the outer tube assembly being slidable; The inner tube assembly is disposed within the inner cavity of the outer tube assembly; A bracket is mounted on the outside of the inner tube assembly; A dual-cavity connector is disposed on the outer tube assembly, the dual-cavity connector comprising: The first cavity has an inclined guiding structure, which allows the guidewire to move along the guiding structure and slide out from the side of the first cavity toward the outlet; The second cavity, which slides with the inner tube assembly, is used to provide guidance and restrict the rotation of the inner tube assembly relative to the outer tube assembly; The first cavity and the second cavity are not connected.

2. The rapid exchange support conveying system according to claim 1, characterized in that, A fitting gap is provided between the inner wall of the second cavity and the outer wall of the inner tube assembly; and the cross-sectional shape of the inner wall of the second cavity is consistent with the cross-sectional shape of the outer wall of the inner tube assembly, wherein the cross-sectional shape is a crescent-shaped groove or an arc-shaped groove.

3. The rapid exchange support conveying system according to claim 1, characterized in that, The guide structure of the first cavity forms an inclination angle of 5° to 30° relative to the length axis of the first cavity.

4. The rapid exchange support conveying system according to claim 1, characterized in that, The inner tube assembly has a sliding groove in the middle section, and the length of the sliding groove is not less than the length of the bracket.

5. The rapid exchange support conveying system according to claim 1, characterized in that, The groove is formed by any of the following methods: machining, laser cutting, embossing, or splicing.

6. The rapid exchange support conveying system according to claim 1, characterized in that, The dual-cavity connector is positioned within a range of 100mm to 350mm from the farthest end of the outer tube assembly.

7. The rapid exchange support conveying system according to claim 1, characterized in that, The dual-cavity connector is made of a polymer material with low frictional resistance and biocompatibility, including Pebax or PA materials.

8. The rapid exchange support conveying system according to claim 1, characterized in that, The dual-cavity connector is fixedly connected to the outer tube assembly by hot-melt welding or laser welding.

9. The rapid exchange support conveying system according to claim 1, characterized in that, The inner tube assembly is made of high-temperature resistant, high-strength polymer materials, including PEEK material.

10. The rapid exchange support conveying system according to claim 1, characterized in that, The outer tube assembly includes a distal outer tube and a proximal outer tube, wherein the outer diameter of the distal outer tube is larger than the outer diameter of the proximal outer tube.

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