Catheter assembly and carotid artery bypass system
By designing a controllable catheter assembly and utilizing the expansion and contraction states of the deformable tube and the deformable body, the problems of guidewire positioning deviation and unstable fixation caused by the space occupied by the existing carotid artery bypass system in the vascular lumen were solved, achieving effective operation and stable positioning of the common carotid artery segment and reducing surgical risks.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- AFFILIATED HUSN HOSPITAL OF FUDAN UNIV
- Filing Date
- 2026-03-23
- Publication Date
- 2026-05-26
Smart Images
Figure CN122075893A_ABST
Abstract
Description
Technical Field
[0001] This application relates to medical devices, and in particular to catheter assemblies and carotid artery bypass systems. Background Technology
[0002] Transcarotid artery revascularization (TCAR) is a procedure that combines open surgery with interventional radiology. Its core principle is to make a small incision above the clavicle in the neck and directly puncture the common carotid artery (CCA). An external shunt is established between the carotid artery and the femoral vein, utilizing the arteriovenous pressure gradient to achieve high-flow reverse blood flow. In this state, plaque fragments generated during the procedure are carried by the reverse blood flow into an external filter, thereby reducing the risk of stroke during the procedure.
[0003] However, existing carotid bypass systems are too long. Once fully inserted into the common carotid artery, they occupy a significant amount of space within the vessel lumen, shortening the effective endovascular segment available for guidewire manipulation and stent delivery. This can easily lead to guidewire passage difficulties or stent positioning deviations. Furthermore, when the sheath is inserted through a small incision in the neck during surgery, relying on sutures and external fixation, there is still a risk of sheath displacement if the patient's position changes or the surgeon accidentally touches it. If it dislodges, it will interrupt the backflow circuit, increasing the surgical risk. Summary of the Invention
[0004] Therefore, it is necessary to provide a catheter assembly and a carotid artery bypass system to address the aforementioned technical problems.
[0005] This application provides a catheter assembly, the catheter assembly comprising:
[0006] Internal catheter;
[0007] An external conduit, which is movably sleeved outside the internal conduit;
[0008] A deformable tube is movably sleeved outside the inner conduit; the distal end of the deformable tube is connected to the inner conduit, the proximal end of the deformable tube is connected to the outer conduit, and at least a portion of the deformable tube has axial expansion and contraction function.
[0009] A deformable body is movably sleeved outside the deformable tube, the distal end of the deformable body is connected to at least one of the deformable tube and the inner conduit, the proximal end of the deformable body is connected to at least one of the deformable tube and the outer conduit, and at least a portion of the structure of the deformable body has a contracted state and an expanded state.
[0010] In one embodiment, the deformable tube is configured to extend and retract axially with the deformable tube to transition between the contracted state and the expanded state.
[0011] In one embodiment, the deformable tube is configured to transition from the contracted state to the expanded state as the deformable tube gradually shortens axially; and / or,
[0012] The deformation type is configured to transition from the expanded state to the contracted state as the deformation tube gradually elongates axially; and / or
[0013] The minimum axial length of the deformation tube is reduced by 50% to 80% relative to the maximum axial length of the deformation tube; and / or,
[0014] The radial dimension of the deformable form in the contracted state is smaller than its radial dimension in the expanded state; and / or,
[0015] The deformable shape has a larger axial dimension in the contracted state than in the expanded state; and / or,
[0016] The radial dimension of the deformable shape gradually decreases from the center to both ends in the expanded state.
[0017] In one embodiment, the deformable tube is configured as a telescopic bellows; and / or,
[0018] The deformable shape is configured as a mesh structure; and / or,
[0019] The material of the deformable form is configured as nickel-titanium metal.
[0020] In one embodiment, at least a portion of the inner conduit and the deformable tube are flexible.
[0021] In one embodiment, the catheter assembly includes:
[0022] At least one control wire is connected to the distal end of at least one of the inner conduit, the deformable tube, and the deformable tube, for controlling the bending of at least a portion of the inner conduit and the deformable tube.
[0023] In one embodiment, the inner catheter has an axial bore in its wall, the control wire is movably inserted through the axial bore, and the distal end of the control wire is connected to the distal end of the inner catheter.
[0024] In one embodiment, the catheter assembly includes:
[0025] An end member having an end hole, wherein the distal end of at least one of the inner conduit, the deformable tube, and the deformable tube is connected to the end member, and the lumen of the inner conduit communicates with the end hole; and / or,
[0026] An outer sheath, which is movably fitted over the outside of the outer conduit; and / or,
[0027] A locking assembly, connected to the inner catheter and the outer catheter, for locking and releasing the relative position between the inner catheter and the outer catheter; and / or,
[0028] A handle assembly connected to the inner catheter and the outer catheter for at least controlling the relative movement between the inner catheter and the outer catheter; and / or,
[0029] A guide wire, which is movably inserted into the lumen of the inner catheter.
[0030] In one embodiment, the deformable part is configured as a deformable metal mesh, the distal end of which is embedded in the end member and the proximal end of which is embedded in the external conduit.
[0031] This application provides a carotid artery bypass system, which includes the catheter assembly.
[0032] In the aforementioned catheter assembly and carotid bypass system, when the carotid bypass system is inserted into the arterial canal, the operator can actively control the shortening of the deformable tube at an appropriate time, thereby increasing the effective working window of the common carotid artery (CCA) segment (i.e., the distance from the distal end of the outer sheath to the origin of the carotid artery lesion). The wide range of extension and contraction can dynamically match the length of the common carotid artery lesion, covering most clinical cases of carotid artery stenosis. Furthermore, the operator can actively control the contraction and expansion states of the deformable tube at appropriate times, utilizing the expansion state to appropriately adhere to the vessel wall, forming a mechanical anchoring point on the vessel wall, effectively resolving the problem of unexpected slippage of the carotid neuroprotective system relative to the common carotid artery. Attached Figure Description
[0033] Figure 1 This is a partial structural plan view of a catheter assembly provided in one embodiment of this application.
[0034] Figure 2 This is a partial structural plan view of a catheter assembly provided in one embodiment of this application from another perspective.
[0035] Figure 3 A plan view of the use state of a catheter assembly provided in one embodiment of this application.
[0036] Figure 4For example Figure 3 The diagram shows the AA cross-sectional view of the catheter assembly in use.
[0037] Figure 5 This is a perspective view of the catheter assembly in use according to an embodiment of this application.
[0038] Figure 6 This is a partial structural cross-sectional view of a catheter assembly provided in one embodiment of this application.
[0039] Icon labels:
[0040] 1000, Inner catheter; 2000, Outer catheter; 3000, Deformation tube; 4000, Deformation type; 5000, Control wire; 6000, Outer sheath; 7000, Locking assembly; 1100, Axial wire hole; 1200, End component; 6100, Limiting sheath end cap. Detailed Implementation
[0041] To make the above-mentioned objectives, features, and advantages of this application more apparent and understandable, the specific embodiments of this application are described in detail below with reference to the accompanying drawings. Many specific details are set forth in the following description to provide a thorough understanding of this application. However, this application can be implemented in many other ways different from those described herein, and those skilled in the art can make similar modifications without departing from the spirit of this application. Therefore, this application is not limited to the specific embodiments disclosed below.
[0042] In the description of this application, it should be understood that if terms such as "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential" appear, these terms indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this application.
[0043] Furthermore, where the terms "first" and "second" appear, these terms are for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined with "first" or "second" may explicitly or implicitly include at least one of that feature. In the description of this application, where the term "multiple" appears, "multiple" means at least two, such as two, three, etc., unless otherwise explicitly specified.
[0044] In this application, unless otherwise expressly specified and limited, the terms "installation," "connection," "joining," and "fixing," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components, unless otherwise expressly limited. Those skilled in the art can understand the specific meaning of the above terms in this application based on the specific circumstances.
[0045] In this application, unless otherwise expressly specified and limited, the use of descriptions such as "above" or "below" the second feature indicates that the first and second features are in direct contact or indirect contact via an intermediate medium. Furthermore, "above," "on top of," and "over" the second feature can mean that the first feature is directly above or diagonally above the second feature, or simply that the first feature is at a higher horizontal level than the second feature. Similarly, "below," "below," and "under" the second feature can mean that the first feature is directly below or diagonally below the second feature, or simply that the first feature is at a lower horizontal level than the second feature.
[0046] It should be noted that if an element is referred to as being "fixed to" or "set on" another element, it can be directly on the other element or there may be an intervening element. If an element is considered to be "connected to" another element, it can be directly connected to the other element or there may be an intervening element. If so, the terms "vertical," "horizontal," "upper," "lower," "left," "right," and similar expressions used in this application are for illustrative purposes only and do not represent the only possible implementation.
[0047] To more clearly describe the structure of the catheter assembly and carotid artery bypass system provided in this application, the term "distal" is defined herein as the end furthest from the operator during the surgical procedure, and "proximal" as the end closest to the operator during the surgical procedure. Unless otherwise defined, all technical and scientific terms used in this application have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The terminology used in this application's specification is for the purpose of describing particular embodiments only and is not intended to be limiting of this application.
[0048] like Figures 1 to 6As shown, this application provides a carotid artery bypass system, which includes a catheter assembly consisting of an inner catheter 1000, an outer catheter 2000, a deformable tube 3000, and a deformable tube 4000, all connected together. The outer catheter 2000 is movably fitted outside the inner catheter 1000, the deformable tube 3000 is movably fitted outside the inner catheter 1000, and the deformable tube 4000 is movably fitted outside the deformable tube 3000. The distal end of the deformable tube 3000 is connected to the inner catheter 1000, and the proximal end of the deformable tube 3000 is connected to the outer catheter 2000. At least a portion of the deformable tube 3000 has axial extension / retraction capabilities, allowing for controllable axial elongation or shortening during the procedure. The distal end of the deformable tube 4000 is connected to at least one of the deformable tube 3000 and the inner catheter 1000, and the proximal end of the deformable tube 4000 is connected to at least one of the deformable tube 3000 and the outer catheter 2000. At least a portion of the structure of the deformable tube 4000 has a contracted state and an expanded state, and can be controlled to switch between the contracted state and the expanded state during the operation.
[0049] Regarding the issues of guidewire passage difficulties and positioning deviations in existing carotid bypass systems, the applicant found that although existing carotid bypass systems have a relatively short design length, such as 11 cm, this fixed working length is still too long for some patients with very short necks or low carotid bifurcation locations. Once the carotid bypass system is fully inserted into the common carotid artery, it occupies a significant amount of space within the vessel lumen, reducing the effective endovascular segment available for guidewire manipulation and stent delivery to only 5 to 8 mm. This limitation is particularly pronounced when treating proximal or long carotid artery lesions and is the root cause of guidewire passage difficulties or stent positioning deviations.
[0050] In this regard, when the carotid artery bypass system provided in this application is inserted into the artery, the operator can actively control the extension or shortening of the deformable tube 3000 at an appropriate time. The degree of extension and shortening can be designed according to actual needs. For example, in one embodiment, the length of the deformable tube 3000 when shortened to its minimum axial length can be limited to 50% to 80% compared to the length of the deformable tube 3000 when extended to its maximum axial length. For example, the length of the deformable tube 3000 when shortened to its minimum axial length can be reduced by 50%, 55%, 60%, 65%, 70%, 75%, or 80% compared to the length of the deformable tube 3000 when extended to its maximum axial length. The wide range of extension and shortening can dynamically match the length of the common carotid artery lesion, covering most clinical cases of carotid artery stenosis.
[0051] For example, with this flexibility, the conventional 2.5cm endoluminal segment length can be shortened to 1.0cm, thereby increasing the effective working window of the common carotid artery (CCA) segment (i.e., the distance from the distal end of the outer sheath 6000 to the origin of the carotid artery lesion). The deformable tube 3000 can be designed with flexibility in its entirety or only in a portion of its segment; this can be designed according to actual needs by those skilled in the art, and is not limited here. Furthermore, the polymer material of the flexible segment of the deformable tube 3000 can be designed as a medical implant material, such as PTFE (polytetrafluoroethylene), PFA (perfluoroalkoxy resin), FEP (fluorinated ethylene propylene copolymer), silicone, etc.
[0052] In addition, the applicant found that although the existing carotid artery bypass system can be positioned by means of sutures and external fixation, such fixation methods still have the risk of displacement. For example, when the patient's position changes or the surgeon accidentally touches the device during the operation, the outer sheath 6000 of the carotid artery bypass system cannot be in a very stable position. Once the carotid artery bypass system dislodges, it will cause the backflow circuit to be interrupted, which will significantly increase the risk of surgical operation.
[0053] To address this, when the carotid artery bypass system provided in this application enters the artery, the operator can actively control the contraction and expansion states of the deformer 4000 at appropriate times. The degree of contraction and expansion can be designed according to actual needs to dynamically match the size of the common carotid artery, covering most clinical cases of carotid artery stenosis. Therefore, when the carotid artery bypass system reaches the predetermined position, the operator actively controls the deformer 4000 to change from a contraction state to an expansion state. By using the radial dimension of the deformer 4000 in the expansion state to match the current size of the common carotid artery, and by utilizing the expansion state of the deformer 4000 to properly adhere to the inner wall of the vessel, a mechanical anchoring point can be formed on the inner wall of the vessel, which can effectively solve the problem of unexpected slippage of the carotid artery nerve protection system relative to the common carotid artery.
[0054] It should be noted that the telescopic control of the aforementioned deformation tube 3000 and the contraction or expansion control of the deformation device 4000 can be controlled individually or in conjunction. For example, the operator can use different control mechanisms to individually control the telescopic control of the deformation tube 3000 at appropriate times, and individually control the deformation device 4000 to switch between contracted and expanded states. The control of the deformation tube 3000 and the deformation device 4000 can be selected according to specific control requirements using various mechanical control methods such as wire harness control, fluid filling control, screw mechanism control, lead screw drive control, and telescopic device control. Those skilled in the art can choose according to actual needs, and no limitation is made here.
[0055] In addition, the telescopic control of the aforementioned deformation tube 3000 and the contraction or expansion control of the deformation form 4000 can also be designed as a mutually linked control. That is, when one of the deformation tubes 3000 or the deformation form 4000 is controlled by a set of control mechanisms, the other will also be controlled to change accordingly. For example, in one embodiment, the deformation form 4000 can be configured to switch between a contracted state and an expanded state as the deformation tube 3000 axially telescopics. That is, when the surgeon controls the extension or shortening of the deformation tube 3000 during the operation, based on the linkage design between the deformation tube 3000 and the deformation form 4000, the deformation form 4000 can be switched between a contracted state and an expanded state simultaneously.
[0056] For example, in one embodiment, the deformer 4000 can be configured to transition from a contracted state to an expanded state as the deformer tube 3000 gradually shortens axially. Therefore, once the carotid artery bypass system reaches the predetermined position, the operator can actively control the axial shortening of the deformer tube 3000. During the shortening process, the deformer 4000 also gradually transitions from a contracted state to an expanded state, changing from a smaller radial dimension in the contracted state to a larger radial dimension for the transition to the expanded state, and from a larger axial dimension in the contracted state to a smaller axial dimension for the transition to the expanded state. Simultaneously, as the deformer 4000 transitions to the expanded state, its radial dimension gradually decreases from the center to both ends.
[0057] Based on the coordinated changes between the deformable tube 3000 and the deformable shaper 4000, when the carotid artery bypass system reaches the predetermined position, the operator controls the axial shortening of the deformable tube 3000 to create a larger effective working window for operation. Simultaneously, the expansion of the deformable shaper 4000 can be used to anchor the current position, simultaneously determining the position of the carotid artery nerve protection system. This fixes the position of the carotid artery nerve protection system and solves the problems of expanding the effective working window and avoiding unexpected slippage. At this time, the expansion and contraction amplitude of the deformable tube 3000 is directly proportional to the contraction and expansion amplitude of the deformable shaper 4000; that is, the greater the expansion and contraction amplitude of the deformable tube 3000, the greater the contraction and expansion amplitude caused by pressure at both ends of the deformable shaper 4000.
[0058] When it is necessary to withdraw the carotid nerve protection system, the operator can still simultaneously control the coordinated movement of the deformable tube 3000 and the deformable shape 4000, that is, actively control the axial extension of the deformable tube 3000. During the extension of the deformable tube 3000, the deformable shape 4000 will also gradually return from the expanded state to the contracted state. The larger radial dimension of the deformable shape 4000 in the expanded state will gradually return to the smaller radial dimension for the transition to the contracted state, and the smaller axial dimension in the expanded state will gradually return to the larger axial dimension for the transition to the contracted state. At the same time, when the deformable shape 4000 returns to the contracted state, it presents a tubular state with the radial dimension and axial dimension roughly consistent.
[0059] The deformable tube 3000 can be configured with various structural designs to achieve flexible axial deformation, and the deformable tube 4000 can also be configured with various structural designs to achieve flexible state changes. For example, in one embodiment, the deformable tube 3000 can be configured as a telescopic bellows, which, based on its corrugated design, enables flexible axial expansion and contraction. The deformable tube 4000 can be configured as a mesh structure, which can be achieved through various methods such as weaving and laser cutting. The deformable tube 4000 can be made of safe materials such as nickel-titanium metal, which are primarily used in medical applications, and is not limited thereto.
[0060] Regarding the issue that existing carotid artery bypass systems are prone to pressing against the vessel wall, scraping off plaque, or causing iatrogenic dissection, the applicant found that the cause of these problems is that existing carotid artery bypass systems cannot dynamically adjust in real time according to the actual tortuosity of the patient's blood vessels. When there are anatomical variations in the blood vessels, the distal end of the carotid artery bypass system is very likely to press against the vessel wall, scraping off plaque, or causing iatrogenic dissection.
[0061] In response, the carotid artery bypass system of this application further designs at least a portion of the inner catheter 1000 and the deformable tube 3000 to have suitable bending capabilities during the structural design. For example, depending on the bending requirements during the operation, some or all of the inner catheter 1000 and the deformable tube 3000 can be designed to have bending capabilities. Moreover, the degree of bending can be designed according to the requirements during the operation. In one embodiment, the bending capability of the inner catheter 1000 and the deformable tube 3000 can be designed to be between 1 degree and 40 degrees. For example, the inner catheter 1000 and the deformable tube 3000 can have bending capabilities of 10 degrees, 15 degrees, 20 degrees, 25 degrees, 30 degrees, 35 degrees, and 40 degrees.
[0062] The bending of the inner catheter 1000 and the deformation tube 3000 can be achieved in various ways. For example, the bending of the inner catheter 1000 can be controlled, thereby causing the deformation tube 3000 to bend. Alternatively, the bending of the deformation tube 3000 can be controlled, thereby causing the inner catheter 1000 to bend. Alternatively, the bending of the inner catheter 1000 and the deformation tube 3000 can be controlled simultaneously. In one embodiment, the catheter assembly may include a control wire 5000 connected to the distal end of at least one of the inner catheter 1000, the deformation tube 3000, and the deformation tube 4000, for controlling the bending of at least a portion of the inner catheter 1000 and the deformation tube 3000. Preferably, the control wire 5000 can be used to connect to the distal end of the inner catheter 1000 for controlling the bending of at least a portion of the inner catheter 1000 and the deformation tube 3000.
[0063] There can be one or more control wires 5000, which can be metal wires or high-strength polymer wires. When there is one control wire 5000, the bending of the inner catheter 1000 and the deformation tube 3000 can be controlled in one direction. When there are multiple control wires 5000, they can be distributed at different circumferential positions of the inner catheter 1000 and the deformation tube 3000, thereby achieving multi-directional bending of the inner catheter 1000 and the deformation tube 3000 to adapt to different bending requirements during surgery. In one embodiment, the inner catheter 1000 may have an axial wire hole 1100 in its wall, and the control wire 5000 is movably inserted through the axial wire hole 1100, with the distal end of the control wire 5000 connected to the distal end of the inner catheter 1000. Therefore, by using the axial line hole, a limit can be formed at a specific circumferential position of the inner conduit 1000, and by using the control wire 5000, the bending control of the inner conduit 1000 and the deformation tube 3000 in a predetermined direction can be stably realized.
[0064] In addition, the catheter assembly may also include components such as an end piece 1200, an outer sheath 6000, a locking assembly 7000, a handle assembly, and a guide wire. The end piece 1200 has an end hole, and the distal end of at least one of the inner catheter 1000, the deformable tube 3000, and the deformable part 4000 is connected to the end piece 1200. The lumen of the inner catheter 1000 communicates with the end hole, thereby allowing the guide wire to be movably inserted through the lumen of the inner catheter 1000 and the end hole of the end piece 1200 for guiding the advancement of the carotid artery nerve protection system within the body. Preferably, the inner catheter 1000 can be connected to the end piece 1200. In one embodiment, the deformable part 4000 is configured as a deformable metal mesh, such as the aforementioned nickel-titanium metal mesh. The distal end of the metal mesh is embedded in the end piece 1200, and the proximal end of the metal mesh is embedded in the outer catheter 2000; this embedding method improves connection stability. In addition, it can be reinforced by fixing methods such as welding and bonding.
[0065] The outer sheath 6000 is movably fitted over the outer catheter 2000, and a limiting cap 6100 can be provided at the distal end of the outer sheath 6000 for limiting contact with the skin externally, thus limiting the puncture depth. The locking assembly 7000 can be connected to the inner catheter 1000 and the outer catheter 2000 to lock and release the relative position between them, thereby ensuring that their relative positions remain unchanged. When the carotid nerve protection system reaches the predetermined position and completes the deformation of the deformable tube 3000 and the deformable shaper 4000, the locking assembly 7000 locks the inner catheter 1000 and the outer sheath 6000, thereby locking the deformation state of the deformable tube 3000 and the deformable shaper 4000. Furthermore, while assisting in the limiting function, it can also be used to prevent unintended radial expansion of the deformable shaper 4000 within the blood vessel.
[0066] For example, the locking assembly 7000 may include a rotary Tuohy-Borst silicone valve integrated into the outer conduit 2000. When not tightened, it allows components such as the inner conduit 1000 to pass through the inner cavity of the outer conduit 2000. After rotation, the tightness of the built-in silicone ring can be adjusted, thereby locking the inner conduit 1000 and other components inside. Therefore, the inner conduit 1000 and the outer conduit 2000 can be locked by rotating the rotating handle of the outer conduit 2000.
[0067] The handle assembly can be connected to the inner conduit 1000 and the outer conduit 2000 to at least control the relative movement between the inner conduit 1000 and the outer conduit 2000. Since the deformable tube 3000 and the deformable shape 4000 are assembled between the inner conduit 1000 and the outer conduit 2000, controlling the axial relative movement between the inner conduit 1000 and the outer conduit 2000 can realize the axial extension and contraction of the deformable tube 3000, as well as the conversion between the contracted state and the expanded state of the deformable shape 4000, which will not be elaborated here.
[0068] Furthermore, the handle assembly can also control the control wire 5000 extending from the proximal end, using the control wire 5000 to control the bending of the inner conduit 1000 and the deformation tube 3000. For example, the handle assembly can use a commonly used interventional bending sheath mechanical transmission design to tension and relax the control wire 5000, corresponding to changes in the bending angle of the inner conduit 1000 and the deformation tube 3000, such as a threaded transmission mechanism or a push-pull slider mechanism. Similar mechanical transmission structures can be controlled by external finger manipulation, such as flicking or sliding, to pull or relax the internal control wire 5000, achieving bending control.
[0069] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.
[0070] The embodiments described above are merely illustrative of several implementation methods of this application, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the patent application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this patent application should be determined by the appended claims.
Claims
1. A catheter assembly, characterized in that, The catheter assembly includes: Internal catheter; An external conduit, which is movably sleeved outside the internal conduit; A deformable tube is movably sleeved outside the inner conduit; the distal end of the deformable tube is connected to the inner conduit, the proximal end of the deformable tube is connected to the outer conduit, and at least a portion of the deformable tube has axial expansion and contraction function. A deformable body is movably sleeved outside the deformable tube, the distal end of the deformable body is connected to at least one of the deformable tube and the inner conduit, the proximal end of the deformable body is connected to at least one of the deformable tube and the outer conduit, and at least a portion of the structure of the deformable body has a contracted state and an expanded state.
2. The catheter assembly according to claim 1, characterized in that, The deformation type is configured to extend and retract axially with the deformation tube to transition between the contracted state and the expanded state.
3. The catheter assembly according to claim 2, characterized in that, The deformation type is configured to transition from the contracted state to the expanded state as the deformation tube gradually shortens axially; and / or, The deformation type is configured to transition from the expanded state to the contracted state as the deformation tube gradually elongates axially; and / or The minimum axial length of the deformation tube is reduced by 50% to 80% relative to the maximum axial length of the deformation tube; and / or, The radial dimension of the deformable form in the contracted state is smaller than its radial dimension in the expanded state; and / or, The deformable shape has a larger axial dimension in the contracted state than in the expanded state; and / or, The radial dimension of the deformable shape gradually decreases from the center to both ends in the expanded state.
4. The catheter assembly according to claim 1, characterized in that, The deformable tube is configured as a telescopic bellows; and / or, The deformable shape is configured as a mesh structure; and / or, The material of the deformable form is configured as nickel-titanium metal.
5. The catheter assembly according to claim 1, characterized in that, The inner conduit and the deformable tube are flexible.
6. The catheter assembly according to claim 5, characterized in that, The catheter assembly includes: At least one control wire is connected to the distal end of at least one of the inner conduit, the deformable tube, and the deformable tube, for controlling the bending of at least a portion of the inner conduit and the deformable tube.
7. The catheter assembly according to claim 6, characterized in that, The inner catheter has an axial hole in its wall, and the control wire is movably inserted through the axial hole, with the distal end of the control wire connected to the distal end of the inner catheter.
8. The catheter assembly according to claim 1, characterized in that, The catheter assembly includes: An end member having an end hole, wherein the distal end of at least one of the inner conduit, the deformable tube, and the deformable tube is connected to the end member, and the lumen of the inner conduit communicates with the end hole; and / or, An outer sheath, which is movably fitted over the outside of the outer conduit; and / or, A locking assembly, connected to the inner catheter and the outer catheter, for locking and releasing the relative position between the inner catheter and the outer catheter; and / or, A handle assembly connected to the inner catheter and the outer catheter for at least controlling the relative movement between the inner catheter and the outer catheter; and / or, A guide wire, which is movably inserted into the lumen of the inner catheter.
9. The catheter assembly according to claim 8, characterized in that, The deformable part is configured as a deformable metal mesh, the distal end of which is embedded in the end member and the proximal end of which is embedded in the external conduit.
10. A carotid artery bypass system, characterized in that, The carotid artery bypass system includes the catheter assembly as described in any one of claims 1-9.