CN216124619U

CN216124619U - Novel covered stent

Info

Publication number: CN216124619U
Application number: CN202120169229.3U
Authority: CN
Inventors: 李彪; 吕世文; 胡晓明; 董娟; 陈超
Original assignee: Ningbo Diochange Medical Technology Co Ltd
Current assignee: Ningbo Diochange Medical Technology Co Ltd
Priority date: 2021-01-21
Filing date: 2021-01-21
Publication date: 2022-03-25
Anticipated expiration: 2031-01-21

Abstract

The utility model provides a covered stent, which comprises a support frame and a thin film body, wherein the support frame is a wavy or net-shaped structure formed by a plurality of elastic support rods in a surrounding way, and comprises a near-end support frame, a waist support frame and a far-end support frame from near to far, and the waist support frame is integrally in a hollow tubular shape. The film body comprises a film A and a film B, the film A is a micropore or nonporous structure, the aperture or node distance of the film A is not more than 60 mu m, and the film A at least covers the inner surface of the support rod of the waist support frame; the membrane B is a microporous structure, the pore diameter or node distance of the membrane B is larger than that of the membrane A, and the membrane B at least covers the outer surface of the marginal area of the near-end part support frame and/or the far-end part support frame. After the tectorial membrane stent is implanted into a target tissue, the diameter of the lumen can be effectively maintained for a long time, the long-term fixation safety is considered, the percutaneous minimally invasive interventional implantation method is suitable for implantation in a percutaneous minimally invasive interventional way, and compared with similar products in the market, the percutaneous minimally invasive interventional implantation method has higher safety and better long-term shunt effectiveness.

Description

Novel covered stent

Technical Field

The utility model relates to the field of passive instrument treatment of heart failure, in particular to a covered stent which has a differential endothelialization functional design and meets the requirement of percutaneous minimally invasive intervention approach implantation.

Background

Heart failure (Heart failure) is the end result of various cardiovascular events and the cumulative effect of various cardiac abnormalities. In some heart diseases, the pressure in the left and right heart rooms can be obviously different, for example, in patients with pulmonary hypertension, the continuous right atrial hypertension exists, the right atrial pressure needs to be reduced, otherwise, the right heart is enlarged and fails, and finally, the heart pumping function is reduced, once the clinical manifestations of heart failure appear in cardiovascular patients, the prognosis is poor, the heart failure is heavier, and the death risk is higher. Heart failure is an abnormal change in the structural function of the heart caused by various causes, causing ventricular systolic ejection and/or diastolic filling dysfunction, resulting in a complex group of clinical syndromes, mainly manifested by a decrease in exercise tolerance (dyspnea, fatigue) and fluid retention (pulmonary congestion, systemic congestion and peripheral hematoma).

Interatrial foramen is a palliative method for treating complex heart diseases, and is to establish traffic between the left atrium and the right atrium of a patient by an intervention method, mix blood in the left atrium and the right atrium, adjust hemodynamics to a relatively stable state, transfer pressure between the left atrium and the right atrium, relieve cardiac load, and prevent the patient from suffering from cardiac insufficiency.

The commonly used clinical pore-creating technique generally adopts a puncture sheath to puncture and create pores at the position of the atrial septum, coronary sinus and the like, and uses balloon expansion to enlarge the defect. However, the size of the pore-forming operation cannot be precisely controlled, and the defect site after the operation is naturally closed, and the retraction phenomenon of the pore-forming operation exists, so that the pore-forming operation is quickly closed due to endothelialization, and the shunting function is lost.

NOYA developed by Denuo medical company for solving the problem that pore-forming technique can not control pore-forming size^TMAdjustable atrium shunting device, capable of aligning atrial septumPerforming radiofrequency ablation for creating a hole, the device being an active interventional medical device, but NOYA^TMThe device has no implant at the pore-forming position after the radio frequency ablation, so that the atrial septal tissue at the shunt hole position is not supported, and the shunt hole area is likely to be gradually closed; secondly, the shunting device adopts a grid structure, and the inner surface of a shunting hole formed after radio frequency ablation is uneven, so that the risk of thrombus formation is caused. In addition, active devices involve energy input, which is difficult to compromise and balance with the safety and effectiveness of clinical treatments, and at the same time, the cost of active devices is high and the cost of surgery is expensive.

Similarly, in order to solve the above problems, foreign V-Wave company has developed a room space shunt (venturi, single shunt device) to support the shunt hole formed by the interventional method, so as to avoid the post-operation retraction of the pore-forming. Wherein, the I generation product is provided with a valve which can play a role of one-way shunt, but 14 percent of cases are completely blocked and 36 percent of cases are restenosis after 12 months of follow-up; in order to solve the problems of the I generation product, the V-Wave company is improved and developed into the II generation product in the later period, namely, the valve in the shunt hole is removed, but the product still has the following problems: 1) the Niti alloy frame is also designed with a polymer film which is easy to be coated by endothelium, so that the shunt hole is blocked (the trial-made sample is referred to in the earlier stage, and the blockage of the shunt hole is found in an exploratory animal experiment after 4 months); 2) the bracket is designed into an hourglass shape, a) only the waist is attached to the interatrial septum tissue, the left disc and the right disc are not attached to the interatrial septum tissue, and the bracket has no clamping force on the interatrial septum and is easy to shake under the scouring of blood flow; b) the stent extends deep into the atrium, occupies the atrial volume, is not easy to endothelialize, and can affect hemodynamics in the atrium.

In addition, the Atrial Flow Regulator (AFR) provided by the alcutech company, which is woven from nickel-titanium wires with the prior art technique of being woven in an up-and-down weaving, has a movable grid-like structure, resulting in: a) the device has small supporting force on the position of the shunt hole, so that the shunt hole retracts or gradually closes. In an animal experiment of an AFR product, the shunt hole is blocked when 1 pig is followed up on the third day, and the shunt hole is blocked when the other pig is followed up on 28 days.

b) The length of the disk surface of the AFR product after being compressed into the sheath tube is far longer than the length of the disk surface of the AFR product in a natural state after being released from the sheath tube, but the reversible deformation of the implantable membrane in the prior art is limited, so that the design of a covering membrane (membranes and filaments in all areas are fixedly connected) cannot be adopted; therefore, the metal coverage rate in the product is high, nickel-titanium alloy wires can be directly contacted with blood and the like, so that nickel ions are separated out, the risks of toxicity, sensitization and teratogenicity are finally caused, and the biocompatibility is poor; and also tends to cause complications such as thrombus formation on the disc surface.

c) The AFR product is limited in position between the filaments, when the waist of the AFR product is placed at a target position, due to mutual dragging of the filaments, the left disc and the right disc of the AFR product are difficult to adapt to the uneven shape of the mouth part, a pore area is formed, and the AFR product cannot be completely attached to the target position.

In addition, the NEOVASC Reducer device developed by neovassc corporation, which was introduced from the jugular vein by minimally invasive surgery^TMThe device is implanted in coronary sinus of heart to relieve angina pectoris by reducing the pumping rate of blood flow from coronary sinus of heart, and allowing part of blood to flow back to ventricular wall to increase blood supply to heart. Wherein for Neovasc Reducer^TMIn the device, the middle part is thinner and 3mm, the two ends are thicker and 13mm, and the whole body is in a dumbbell shape. The middle part shunting hole of the device is small and is only 3mm, and the blood flowing through the coronary sinus is venous blood, so that the blood flow speed is low, and the device, particularly the middle part shunting hole is easy to close due to endothelial climbing.

Therefore, designing and developing a covered stent with a differentiated endothelialization function aims to effectively maintain the size of a lumen channel of the covered stent for a long time without causing stenosis or even blockage, and gives consideration to the safety of long-term fixation.

SUMMERY OF THE UTILITY MODEL

The utility model aims to overcome the defects of the prior art, and provides a covered stent, which can effectively maintain the size of a lumen channel of a waist support frame for a long time after the covered stent is implanted into a target tissue, is not narrow or even blocked, gives consideration to the safety of long-term fixation, simultaneously meets the series of functions of percutaneous minimally invasive intervention implantation, and has higher safety and better long-term shunt effectiveness compared with similar products in the market.

The purpose of the utility model is realized by the following technical scheme:

a novel covered stent comprises a support frame and a thin film body, wherein the support frame is a wavy or net-shaped structure formed by a plurality of elastic support rods in a surrounding mode, the support frame comprises a near-end portion support frame, a waist portion support frame and a far-end portion support frame from near to far, the waist portion support frame is integrally in a hollow tubular shape, the thin film body at least comprises a thin film A and a thin film B, the thin film A is in a microporous structure or a nonporous structure, the aperture or node distance of the thin film A is not more than 60 mu m, the thin film A at least covers the inner surfaces of all the support rods of the waist portion support frame, and the inner surfaces are all surfaces of the support rods, which are in contact with fluid; the membrane B is a microporous structure, the aperture or node distance of the membrane B is larger than that of the membrane A, and the membrane B at least covers the outer surfaces of the marginal areas of all the support rods of the proximal end part support frame and/or the distal end part support frame, wherein the outer surfaces are all the surfaces of the support rods contacting with target tissues.

The purpose of the application can be further realized by the following technical scheme:

in one embodiment, the film a is a non-porous structure, the film a covering the inner and outer surfaces of all of the support rods of the lumbar support basket; the membrane B is a microporous structure, the pore diameter or node distance of the membrane B is not more than 200 μm, and the membrane B covers the inner surface and the outer surface of the edge part or all of the support rods of the near-end part support frame and/or the far-end part support frame. The film A and the film B are of an integrated seamless connection structure.

In a preferred embodiment, the pore size or nodal distance of the membrane a is at least 30 μm smaller than the pore size or nodal distance of the membrane B, giving the membrane body a differential endothelialization function.

In a preferred embodiment, the proximal end support frame, the lumbar support frame and the distal end support frame are sequentially and fixedly connected with each other by a plurality of support rods to form a three-dimensional net structure, the stent graft is rotationally symmetric along a central axis m of the lumbar support frame, and the thin film body covers the whole surface of the stent graft, wherein the surface comprises an inner surface and an outer surface of the support frame and a blank part of the three-dimensional net structure, the thin film body is in a flexible sheet shape, and the thickness of the thin film body is between 1 μm and 200 μm. The covered stent is provided with a sheath retracting tolerance structure, the sheath retracting tolerance structure is used for compensating the length difference of the thin film body and the support frame on the central axis of a sheath tube when the covered stent retracts, the sheath retracting tolerance structure comprises a curled structure or a folded structure or a split structure which is arranged on the thin film B, the curled structure or the folded structure enables the thin film body to have 20% -50% of elongation, the split structure is positioned on the blank part of the three-dimensional net structure, the thin film bodies positioned on the two sides of the split structure are physically split, the thin film bodies on the two sides of the split structure can touch or overlap in a natural unconstrained state, and the thin film bodies on the two sides of the split structure are separated from each other in the sheath retracting process.

In a preferred embodiment, the stent graft is provided with a buffer structure on the edge of the support rod of the proximal end support frame and/or the distal end support frame, the buffer structure is on the same surface with the edge area of the support rod of the distal end support frame and/or the proximal end support frame, and the buffer structure is completely covered in the thin film body for reducing the damage of the edge of the support rod to the tissue and avoiding the delamination or peeling between the distal end of the support rod and the thin film body, the thin film B is provided with a spacing structure, the spacing structure is located in the gap area between the buffer structure and the support rod framework, and the spacing structure ensures that the distal end portion of the buffer structure can be elastically deformed relative to the edge of the support frame.

In one embodiment, a buffer structure is arranged on the edge of a support rod of a support frame at the distal end part of the covered stent, and the buffer structure and the support frame are of an integrated structure formed by laser engraving and heat setting of the same shape memory alloy tube; the buffer structure is composed of an even number of buffer rods, and every two adjacent buffer rods are fixedly connected at the far end and are gathered at the connection part of the buffer structure; the near-end area of the buffer rod is provided with a self-adaptive structure; the adaptive structure has anatomical morphology adaptability, the adaptive structure is radially outward from the edge of the far-end supporting frame, then the adaptive structure is bent to obliquely cross the edge of the far-end supporting frame in the proximal direction and extend towards the center of the supporting frame, and the bending angle theta satisfies the following conditions: 90 DEG-175 DEG, or from the edge of the support frame at the distal end part to the outside and then extends in a direction away from the support frame in a curved shape on a plane alpha, and the bending angle theta satisfies: theta is more than or equal to 10 degrees and less than or equal to 135 degrees.

In a preferred embodiment, the stent graft further comprises a reinforcing structure; the reinforcing structure is composed of a plurality of reinforcing rods; the reinforcing rod is fixedly connected with the supporting rod on the proximal end part supporting frame and/or the distal end part supporting frame and is used for reinforcing the abutting force of the edge area of the proximal end part supporting frame and/or the distal end part supporting frame on the atrial septal tissue, and further preventing the supporting frame from shaking or falling off in the releasing process or after the releasing process.

In a preferred embodiment, the stent graft further comprises an anchoring structure; the anchoring structure can generate reversible elastic deformation, has form adaptivity and realizes non-invasive anchoring with target tissues; the anchoring structure includes: an anchoring structure free portion and an anchoring structure connecting portion;

the anchoring structure connecting part is used for fixedly connecting the supporting rod and the anchoring structure; the anchoring structure free portion protrudes out of the outer surface of the support rod in a natural unconstrained state; the anchoring structure free portion has an aspect ratio of between 2 and 50.

In a preferred embodiment, the length of each support rod is no greater than20mm, and the included angle between the adjacent support rods is not more than 120 degrees. The whole covered stent is in a hollow tubular shape or a hollow dumbbell shape, and the definition is as follows: the distance between the distal end surface of the covered stent and the distal end surface of the film A is L₁The distance between the near end surface of the covered stent and the near end surface of the film A is L₂，L₁And L₂The following mathematical relationship is satisfied: 0 < L₁≤10mm，0＜L₂≤10mm；

Or, the whole covered stent is in a flat I shape, the edge area of the support frame at the far end part is provided with a tangent plane alpha, the tangent plane alpha is vertical to the central axis m of the covered stent, the edge area of the support frame at the near end part is provided with a tangent plane beta, the tangent plane beta is vertical to the central axis m of the covered stent, the number of the mesh layers of the mesh structure is 2-4, and the definition is as follows: the maximum outer diameter of the support frame at the far end part is D₁The inner diameter of the waist support frame is D₂The maximum outer diameter of the proximal end part support frame is D₃The maximum diameter of the film A covering the support frame area at the far end part is D₄The maximum diameter of the membrane A covering the area of the proximal end part support frame is D₅Wherein D is₁、D₂、D₃、D₄And D₅The following mathematical relationship is satisfied: d is not less than 15mm₁≤35mm，3mm≤D₂≤15mm，15mm≤D₃≤35mm，D₂＜D₄≤D₁-2mm，D₂＜D₅≤D₃-2mm。

In a preferred embodiment, the material of the film a, the film B, and the film C includes one or more of parylene, titanium nitride, mucopolysaccharide sulfate, ceramic, polyethylene terephthalate, polytetrafluoroethylene, expanded polytetrafluoroethylene, silica gel, polyurethane, and heparin, and the film a, the film B, and the film C are made of the same material.

Compared with the prior art, the utility model has the following outstanding advantages:

1. the utility model provides a covered stent, wherein the surface of a supporting frame of the covered stent is covered or wrapped with a film body, the film body comprises a film A and a film B, the film A is of a non-porous structure or a microporous structure, the aperture or node distance of the film A is not more than 60 mu m, the film A at least covers the inner surfaces of all supporting rods of a waist supporting frame, the film B is of a microporous structure, the film B at least covers the outer surfaces of all supporting rods of the marginal area of a proximal end supporting frame and/or a distal end supporting frame, and the aperture or node distance of the film A is at least 30 mu m smaller than that of the film B, which means that the film body has a differential endothelialization functional design, so that the edge of the proximal end supporting frame and the edge of the distal end supporting frame can play a role in promoting endothelialization to enhance the long-term fixation of the supporting frame at a target position; the rest part of the covered stent used as the implant, particularly the lumbar support frame, can effectively prevent endothelialization, so that the lumen size of the lumbar support frame can be kept for a long time, and the effective purpose of long-term shunt can be achieved.

2. The coverage area of the film A satisfies D₂＜D₄≤D₁-2，D₂＜D₅≤D₃The design of the mathematical relationship is-2, the coverage area of the thin film A for preventing endothelialization can be enlarged to the maximum extent, the effectiveness of the lumbar support frame for preventing endothelialization is further ensured, and the effect of long-term shunt is enhanced.

3. The covered stent provided by the utility model is provided with a sheath retracting tolerance structure which can be a curled structure, a folded structure or a split structure, and when the sheath retracting tolerance structure is used for compensating the sheath retracting of the covered stent, the length difference between the film body and the support frame on the central axis of the sheath tube enables the surface of the support frame to be completely covered with the film body (the film body and the support rod in all regions are fixedly connected) after the covered stent is released to a target position, and the sheath retracting process of the covered stent is not influenced, so that the covered stent is suitable for implantation in a percutaneous minimally invasive intervention way.

4. The edge of the support rod of the proximal end part support frame and/or the distal end part support frame on the covered stent is provided with the buffer structure, and the buffer structure is positioned at the edge area of the support rod of the distal end part support frame and/or the proximal end part support frame and is completely covered in the thin film body, so that the damage of the edge of the support rod to the tissue is reduced, and the delamination or the peeling between the distal end of the support rod and the thin film body is avoided. The gap area between the buffer structure and the support rod framework is provided with a spacing structure, so that the distal end part of the buffer structure can be elastically deformed relative to the edge of the support frame, and the buffer structure and the spacing structure cooperate to enable the buffer structure to play a role in reducing the damage of the edge of the support rod to tissues.

5. The edge of the proximal end part support frame and/or the distal end part support frame of the covered stent provided by the utility model is provided with a reinforcing structure consisting of a plurality of reinforcing rods, the reinforcing rods are fixedly connected with the edge of the distal end part support frame and completely cover the edges in the thin film body, and the design not only avoids the phenomenon that the thin film body folds or collapses after the covered stent is loaded and sheathed for multiple times, so that the endothelialization of the covered stent is accelerated, the long-term fixing safety is enhanced, but also the attaching force of the edge area of the distal end part support frame on target tissues can be enhanced, and the support frame is prevented from shaking or falling off in the releasing process or after the releasing process.

6. The tectorial membrane stent provided by the utility model comprises an anchoring structure, wherein the anchoring structure comprises an anchoring structure free part and an anchoring structure connecting part, the anchoring structure connecting part is used for fixedly connecting a supporting rod and the anchoring structure, the anchoring structure free part protrudes out of the outer surface of the supporting rod in a natural unconstrained state, the length-diameter ratio of the anchoring structure free part is between 2 and 50, the anchoring structure can generate reversible elastic deformation, has form self-adaptability and realizes non-invasive anchoring with target tissues.

7. The buffer structure of the covered stent provided by the utility model is provided with the self-adaptive structure, the self-adaptive structure is positioned in the connection area of the buffer rod and the support rod on the support frame at the far end part, the self-adaptive structure radially faces outwards from the edge of the support frame at the far end part, then the self-adaptive structure obliquely spans the edge of the support frame at the far end part towards the near end direction in a bending shape and extends towards the center of the support frame, and the self-adaptive structure has the following advantages: a) the edge of self-adaptation structure by the distal end portion support frame is radial outwards, then is the edge of curved form line of defence inclined cross distal end portion support frame towards the near-end for self-adaptation structure has great curve arc, makes whole self-adaptation structure all tend to gentle state, makes its at utmost lean on the surface of distal end portion support frame. Therefore, the buffer structure and the support frame are fixedly connected by taking a larger curve arc shape and a more gentle turning form as a self-adaptive structure, the self-adaptive structure is in contact with the edge of the support rod on the support frame at the far end part and the buffer rod are in contact with the target tissue, so that the contact area is greatly increased, the stimulation and damage of the support frame to the target tissue are reduced to the greatest extent, and the condition that the edge of the support rod on the support frame at the far end part is in contact with the tissue in a sharper and sharp form in the prior art, and further the stimulation and inflammatory reaction to the tissue and the physical damage to the tissue are caused by mechanisms such as stress concentration and the like is avoided; b) the self-adaptive structure has the characteristic that the self-adaptive structure is attached to the outer surface of the support frame at the far end part and is not obtrusive relative to the support frame at the far end part, so that the occupied space at a target position is reduced, and the influence on the hemodynamics is greatly reduced. At the same time, the probability of thrombosis on the scaffold is reduced. c) Compared with all the support rods in the edge area of the support frame at the far end part, the self-adaptive structure has a much smaller cross section area and much higher elastic deformability, wherein the cross section area of the self-adaptive structure is not more than half of the cross section area of all the support rods, so that the self-adaptive structure has a certain degree of radial telescopic adjustment function, and can adapt to a smaller surface area, and the adaptive population of the covered stent, especially Asian population and minor population, of the covered stent of the utility model are greatly expanded; of course, the effect on the adjacent tissue at the target site can be minimized or controlled; the adaptive structure has elastic deformation to a certain degree in the axial direction, can adapt to uneven tissues possibly existing in a target area, remarkably improves tissue fitting performance, reduces stimulation and damage of the support frame to the target tissues, and has wide anatomical morphology adaptability; d) as the buffer structure of the adaptive structure, since the adaptive structure is positioned at the far end of the support frame at the far end part, and is bent to extend obliquely across the edge of the support frame at the distal end part towards the proximal direction and towards the center of the support frame, during the gradual deployment of the distal scaffold from the release sheath, or during the pulling back of the distal scaffold that has been sufficiently deployed from the release sheath against the target tissue, when the covered stent may slide off due to improper operation of an operator, the self-adaptive structure can be always clamped on one side of the target tissue, and further form a self-locking structure which can prevent the covered stent from further sliding off, this also means that the adaptive structure and part or all of the distal end support frame are always positioned at one side of the target position, so that the covered stent does not completely slide into the body, and bad time is avoided; therefore, the position of the covered stent can be adjusted for the second time by the operator through subsequent observation images, and finally the covered stent operation can be smoothly carried out and can be safely implanted to the target position.

Drawings

FIG. 1a is a schematic view of a stent graft of one embodiment of the present invention in a hollow tubular configuration with film A covering only the inner surface of the lumbar support basket and film B covering only the outer surfaces of the proximal and distal support baskets;

FIG. 1b is a cross-sectional view of the lumbar support frame of FIG. 1 a;

FIG. 2 is a schematic view of a stent graft according to a first embodiment of the present invention, wherein the stent graft has a hollow tubular structure, and the thin film body covers the entire inner and outer surfaces of the stent graft;

FIG. 3 is a schematic view of a stent graft having a dumbbell-shaped structure and a thin film covering the entire stent graft according to an embodiment of the present invention;

fig. 4a to 4c are schematic views of the sheath-retracting tolerance structure, wherein fig. 4a is a curling structure; FIG. 4b is a pleated structure; FIG. 4c is a segmented structure;

FIG. 5a is a schematic cross-sectional view of the stent graft covering the entire stent graft when the thin film body is in the form of a flexible sheet according to the second embodiment of the present invention;

FIG. 5b is a top view of FIG. 5 a;

FIG. 6 is a schematic view illustrating a film body wrapping a whole stent graft in a winding manner when the film body is in a flexible strip shape according to the second embodiment of the present invention;

FIG. 7 is a schematic view of the stent covered with a cover film according to the second embodiment of the present invention when the film body is a biocompatible film D or coating;

FIGS. 8 a-8 f are schematic views of various cushioning structures of the present invention, wherein FIG. 8a shows an "S" shaped cushioning structure, FIG. 8b shows a "match" shaped cushioning structure, FIG. 8c shows a "J" shaped cushioning structure, FIG. 8d shows the cushioning structure being a wrap head, FIG. 8e shows the cushioning structure being an adaptive structure, and FIG. 8f shows the cushioning structure being another adaptive structure;

FIG. 9a is an embodiment of a reinforcing rod of the present invention;

FIG. 9b is a schematic view of a first embodiment of a second embodiment of the present invention, with a reinforcing structure;

FIG. 10 is a schematic view of a stent graft of the present invention having anchoring structures on the distal end of the stent graft;

FIG. 11 is a schematic view of a stent graft of the present invention having anchoring structures on both the distal scaffold and the proximal scaffold;

FIG. 12a is a microstructure (SEM) of film A of the present invention;

FIG. 12B is a microstructure (SEM) of film B of the present invention;

FIG. 13 is a photograph of a stent graft according to the present invention implanted in a target tissue for 6 months after dissection.

Wherein 1 is a stent graft, 2 is a stent graft, 5 is a thin film body, 6 is a target tissue, 7 is a sheathing tolerance structure, 20 is a distal end portion stent, 21 is a lumbar portion stent, 22 is a proximal end portion stent, 23 is a buffer structure, 24 is a reinforcing structure, 25 is an anchoring structure, 201 is a notch, 210 is a support rod, 211 is a lumbar portion stent lumen, 212 is a connection hole, 213 is a serial coil, 230 is a buffer structure connection portion, 231 is a buffer structure free portion, 232 is a buffer rod, 233 is a spacer structure, 240 is a reinforcing rod, 251 is an anchoring structure free portion, 252 is an anchoring structure connection portion, 30000 is an adaptive structure, 50 is a thin film a, 51 is a thin film B, 52 is a thin film C, 70 is a coiled structure, 71 is a pleated structure, and 72 is a segmented structure.

Detailed Description

The technical solution proposed by the present invention is further described in detail below with reference to the accompanying drawings and specific embodiments. Advantages and features of the present invention will become apparent from the following description and from the claims. It is to be noted that the drawings are in a very simplified form and are not to precise scale, which is provided solely for the purpose of facilitating and distinctly claiming the embodiments of the present invention. In particular, different proportions are often used, as the drawing figures are to be distinguished.

To more clearly describe a stent graft provided by the present invention, the terms "distal" and "proximal" are defined herein, which terms are conventional in the field of interventional medical devices. Specifically, "proximal" refers to the end that is closer to the operator during the procedure, particularly when the stent graft is loaded in the delivery system, and "distal" refers to the end that is further from the operator during the procedure, particularly when the stent graft is loaded in the delivery system.

The utility model will be described in further detail below with reference to the drawings and a number of specific embodiments.

The first embodiment is as follows:

the novel covered stent provided by the utility model comprises a support frame 2 and a thin film body 5, wherein the support frame 2 is a wavy or net-shaped structure formed by a plurality of elastic support rods in a surrounding mode, the support frame 2 comprises a near-end-portion support frame 22, a waist-portion support frame 21 and a far-end-portion support frame 20 from near to far, and the whole waist-portion support frame 21 is in a hollow tubular shape. The surface of the supporting frame 2 is covered or wrapped with a film body 5, the film body 5 comprises the film A50 and the film B51, the film A50 is of a non-porous structure or a microporous structure, the film B51 is of a microporous structure, the pore diameter or node distance of the film A50 is not more than 60 μm, and the film A50 at least covers the inner surfaces of all the supporting rods 210 of the lumbar supporting frame 21, wherein the inner surfaces are all the surfaces of the supporting rods 210 which are in contact with fluid; the membrane B51 has a greater aperture or nodal distance than the membrane a50, and the membrane B51 covers at least the outer surfaces of the edges of all the struts 210 of the proximal and/or

distal end scaffolds

22, 20, wherein the outer surfaces are all the surfaces of the struts 210 that contact the target tissue 6. Since the stent 2 is usually made of metal material, and when directly implanted into the body, it will be in direct contact with blood, and therefore has poor biocompatibility, and also has a certain risk of thrombosis on the surface of the metal stent, for this reason, the surface of the stent 2 needs to be covered with the thin film body 5, and through many tests and studies, when the aperture or the internode distance of the thin film body 5 exceeds 60 μm, cells in the human body, including various cells in the blood, may pass through the thin film body 5 to grow on the surface of the thin film body 5 in an creeping manner, therefore, the surface of the lumbar support 21 is designed to be covered with the thin film a51, and the aperture or the internode distance of the thin film a51 does not exceed 60 μm, and the thin film a51 at least covers the inner surfaces of all the support rods 210 of the lumbar support 21, so as to effectively prevent endothelialization, so that the size of the lumen of the lumbar support basket 21 can be kept for a long time to achieve the purpose of long-term shunt effectiveness.

The stent graft 1 and the thin film body 5 covering the stent graft 2 have various embodiments, and as a simple mode, the stent graft 1 is integrally hollow tubular or hollow dumbbell-shaped, the length of each supporting rod of the stent graft 2 is not more than 20mm, the included angle between adjacent supporting rods 210 is not more than 120 degrees, the thin film A50 or the thin film B51 only covers the inner surface of the lumbar supporting frame 21, and the distance between the distal end surface of the stent graft 1 and the distal end surface of the thin film A50 is L₁The distance between the proximal end face of the covered stent 1 and the proximal end face of the film A50 is L₂L is shown in FIG. 1a and FIG. 1b₁And L₂Should be as small as possible, e.g. L₁And L₂The following mathematical relationship is satisfied as much as possible: 0 < L₁≤10mm，0＜L₂Less than or equal to 10 mm; this design has the following advantages; a) the film A50 prevents endothelialization of the inner surface of the lumbar support basket 21 so that the lumen size of the lumbar support basket 21 is maintained for a long period of time to achieve long term shunt effectiveness; b) the outer surfaces of the edge regions of all the support rods 210 of the proximal end portion support frame 22 and the edge regions of all the support rods 210 of the distal end portion support frame 20 are covered with the film B, and the outer surfaces of the edge regions are covered with the film BThe film B51 is a microporous structure, the pore diameter or node distance of the film B51 is larger than that of the film A50, but the pore diameter or node distance of the film B51 is not more than 200 μm, so that the marginal zone of the stent 2 can promote endothelialization, and further the fixed connection of the proximal end and the distal end of the stent graft 1 and the target tissue 6 is realized, and the long-term fixation of the stent graft 2 at the target position is enhanced.

In another embodiment, the proximal end support frame 22, the lumbar support frame 21 and the distal end support frame 20 are sequentially and fixedly connected to each other by a plurality of support rods 210 to form a three-dimensional net structure, the stent graft 1 is rotationally symmetric along the central axis m of the lumbar support frame 21, and the thin film body 5 covers the entire surface of the stent graft 1. The film body 5 is a flexible sheet, and the film body 5 includes the film a50 and the film B51. Wherein the film A50 is of a non-porous structure or a microporous structure, as shown in figure 12a, the film A50 covers the inner and outer surfaces of all the supporting bars 210 of the lumbar support basket 21. The membrane B51 is a microporous structure, as shown in fig. 12B, the membrane B51 has a pore size or node distance of not more than 200 μm, and the membrane B51 covers at least the surface of all the struts 210 in the marginal region of the proximal scaffold 22 and/or the distal scaffold 20, as shown in fig. 2 and 3. Preferably, the pore size or node distance of the membrane a50 is at least 30 μm smaller than the pore size or node distance of the membrane B51, giving the membrane body 5a significantly different endothelialization function. More preferably, the membrane B51 covers at least the edges of the proximal scaffold 22 and/or the support rods 210 of the distal scaffold 20, such that the edges of the proximal scaffold 22 and the edges of the distal scaffold 20 can act as a pro-endothelialization to enhance the long-term fixation of the scaffold 2 at the target site; the film A50 on the lumbar support basket 21 can effectively prevent endothelialization, so that the lumen size of the lumbar support basket 21 can be maintained for a long time, and the purpose of effectiveness of long-term shunt can be achieved.

Film A50 with film B51's material includes one or several kinds in poly-p-xylene, titanium nitride, mucopolysaccharide sulfate, pottery, polyethylene glycol terephthalate, polytetrafluoroethylene, expanded polytetrafluoroethylene, silica gel, polyurethane, heparin, through shaping technology such as cementing, hot joint, coating, foaming, film A50 can form microporous structure or nonporous structure, film B51 forms microporous structure, if film A50 with film B51 is same material, then film A50 with film B51 can become integral type seamless connection structure, and above-mentioned design has following advantage: a) the surface of the stent 2 adopts the thin film bodies 5 with different pore sizes, namely, the thin film bodies 5 are endowed with a differential endothelialization function design, especially for the purpose of considering the clinical use effect of the differential endothelialization function, the edge of the proximal end portion stent 22 and the edge area of the distal end portion stent 20 can play a role in promoting endothelialization so as to enhance the long-term fixation of the stent 2 at a target position, and the rest part of the stent graft 1 as an implant, especially the lumbar portion stent 21, can effectively prevent endothelialization, so that the lumen of the lumbar portion stent 21 can be kept unobstructed for a long time, and the purpose of long-term shunt can be achieved; b) the membrane a50 and the membrane B51 may be an integral seamless joined structure such that the joined area of the membrane a50 and the membrane B51 is a smooth transition to avoid thrombosis and interference with the delivery and retraction sheath; of course, in order to control the influence of the retraction/release sheath to the minimum as possible, the thickness of the film a50 and the film B51 is preferably as thin as possible, for example, 1 to 200 μm.

In this embodiment, the covered stent 1 is provided with a sheath retracting tolerance structure 7, the sheath retracting tolerance structure 7 has a certain reversible deformation, and when the covered stent 1 retracts the sheath, the length difference between the thin film body 5 and the support frame 2 on the central axis of the sheath tube can be compensated, so that the surface of the support frame 2 can cover the thin film body 5 (the thin film bodies 5 and the support rods 210 in all regions are fixedly connected), the sheath retracting process of the covered stent 1 is not affected, and the implantation of a percutaneous puncture (such as a blood vessel, such as a femoral vein) minimally invasive intervention way is satisfied.

In one embodiment, the sheathing tolerance structure 7 is a coil structure 70 and/or a wrinkle structure 71, and the coil structure 70 and/or the wrinkle structure 71 are disposed on the film B51, as shown in fig. 4a and 4B, so that the film body 5 has an elastic deformation (elongation) of 20% to 50%, which can compensate for the length difference between the film body 5 and the stent 2 on the central axis of the sheath tube when the stent graft 1 is sheathed.

In another embodiment, the sheathing tolerance structure 7 is a dividing structure 72, the dividing structure 72 is located on the film B51, as shown in fig. 4c, and also corresponds to a blank portion (non-support rod region) of the three-dimensional net-shaped structure, and the dividing structure 72 is configured such that the film bodies 5 on both sides of the dividing structure 72 are physically divided. After the covered stent 1 is placed at a target position, under a natural unconstrained state, the edges of the thin film bodies 5 at the two sides of the dividing structure 72 can be touched or overlapped, and the thin film bodies 5 are not influenced to play a preset differential endothelialization function; in the loading and sheath retracting process of the covered stent 1, the thin film bodies 5 at two sides of the dividing structure 72, particularly the adjacent edges, are separated from each other, so that the length difference of the thin film bodies 5 and the supporting frame 2 on the central axis can be compensated, the loading and sheath retracting process of the covered stent 1 is not influenced, and the implantation of a percutaneous puncture minimally invasive intervention way is met.

Example two:

based on the first embodiment, the second embodiment is different from the first embodiment in that: the whole covered stent 1 is in a flat I shape, and the whole surface of the support frame 2 is covered or wrapped with a thin film body 5.

On this basis, as a specific example, the stent graft 1 is an elastic interatrial septum pore-forming stent (i.e., an atrial shunt) that can be placed at the interatrial septum. Specifically, the support frame 2 is a wavy or net-shaped structure fixedly connected with a plurality of elastic support rods 210, the number of layers of the wavy or net-shaped structure is 2-4, the length of each support rod 210 is not more than 20mm, the included angle between adjacent support rods 210 is not more than 120 degrees, and the design can realize the function of a sheath retracting tolerance structure 7 arranged on a thin film body 5 of the covered stent 1 to a certain extent, namely, when the sheath retracting of the covered stent 1 is compensated, the length difference of the thin film body 5 and the support frame 2 on the central axis of a sheath tube, so that the covered stent 1 is ensured to be smoothly loaded and retracted, and the implantation operation in a minimally invasive intervention way is met.

The support frame 2 comprises a near end portion support frame 22 attached to an interatrial septum in a right atrial chamber, a far end portion support frame 20 attached to an interatrial septum in a left atrial chamber and a waist portion support frame 21 arranged between the near end portion support frame 22 and the far end portion support frame 20 and fixedly connected with the near end portion support frame 22 and the far end portion support frame 20 from near to far. The design that a tangent plane alpha exists on the edge area of the proximal end portion support frame 22, the tangent plane alpha is perpendicular to the central axis m of the support frame 2, a tangent plane beta exists on the edge area of the distal end portion support frame 20, and the tangent plane beta is perpendicular to the central axis m of the support frame 2 can enhance the fit between the edge area of the distal end portion support frame 20 and the edge area of the proximal end portion support frame 22 and the target tissue 6, and reduce the stimulation or damage of the edge area of the distal end portion support frame 20 and the edge area of the proximal end portion support frame 22 to the target tissue 6. The whole waist support frame 21 is in a hollow tubular shape, and the inner cavity of the waist support frame 21 enables the left atrium and the right atrium to be in fluid communication, so that shunting of the left atrium and the right atrium is realized.

The whole surface of the supporting frame 2 is covered or wrapped with a film body 5, the film body 5 comprises a film A50 and a film B51, the film A50 is of a non-porous structure, and the film A50 at least covers the surfaces of all supporting rods 210 of the waist supporting frame 21; the film B51 is a microporous structure, and the film B51 covers at least the surface of all the support rods 210 in the marginal region of the proximal end strut 22 and/or the distal end strut 20. The pore size or nodal distance of the membrane a50 and the membrane B51 do not exceed 60 μm, because too large a pore size or nodal distance affects the area of the scaffold 2 itself in contact with the target tissue 6 or blood, and affects its biocompatibility to some extent.

Preferably, the pore size or nodal point distance of the membrane a50 is at least 30 μm smaller than the pore size or nodal point distance of the membrane B51. More preferably, the membrane B51 covers at least the edges of the proximal scaffold 22 and/or the support rods 210 of the distal scaffold 20. This is because the support frame 2 is usually made of shape memory alloy, such as nitinol, when directly implanted into the body, not only increases the area in contact with blood, to a certain extent affects the biocompatibility of the product, but also increases the risk of generating thrombus on the surface of the metal support frame; through a plurality of researches, the design that the surface of the support frame 2 is covered with the thin film body 5 can solve the problem quickly and effectively, and further, the research finds that when the aperture or the internode distance of the thin film body 5 exceeds 30 mu m, various cells in blood easily penetrate through the thin film body 5 and climb on the surface of the thin film body 5 to accelerate endothelialization. Therefore, the surface of the lumbar support basket 21 is designed to be covered with the film A50, and the internode distance of the film A50 is not more than 30 μm, so that the lumen size of the lumbar support basket 21 can be kept for a long time, and the effect of long-term permanent shunt is achieved. All of the support rod 210 surfaces or edge areas of the proximal scaffold 22 and/or the distal scaffold 20 need to be covered or wrapped with the film B51 to promote endothelialization of the covered or wrapped areas to enhance long term immobilization of the scaffold 2 at the target site.

In the first embodiment, the film body 5 is flexible sheet, the film a50 with the film B51 is same macromolecular material, the material includes polyethylene terephthalate, polytetrafluoroethylene, expanded polytetrafluoroethylene, polyurethane, silica gel, through shaping technology such as cementing, hot joint, coating, foaming, makes film a50 forms the cellular structure, the aperture or node distance of cellular structure is 10 μm, the aperture or node distance of film B51 is 45 μm. The support frame 2 is an integrated structure formed by laser engraving and heat setting of the same shape memory alloy pipe. The edges of the distal end portion support frame 20 and the proximal end portion support frame 22 each enclose a circle, wherein the maximum diameter of the distal end portion support frame 20 is D₁The diameter of the proximal end support frame 22 is D₃. The diameter of the inner cavity of the waist support frame 21 is D₂The axial height of the waist support frame 21 is 1mm-15mm, and the waist support frame is thinMembrane A50 has a diameter D covering the largest area on the distal end scaffold 20₄The membrane A50 has a diameter D covering the largest area of the proximal end support basket 22₅Wherein D is₁、D₂、D₃、D₄And D₅The following mathematical relationship is preferably satisfied: d is not less than 15mm₁≤35mm，3mm≤D₂≤15mm，15mm≤D₃≤35mm，D₂＜D₄≤D₁-2，D₂＜D₅≤D₃-2, the membrane B51 covering the remaining area of the distal scaffold 20 and the remaining area of the proximal scaffold 22, wherein the membrane a50 and the membrane B51 are a one-piece seamless joined structure, as shown in fig. 5a, 5B. The above design has the following advantages: a) the surface of the support frame 2 adopts the thin film bodies 5 with different pore sizes, namely the thin film bodies 5 are endowed with the design of differential endothelialization function, particularly the clinical use effect of the differential endothelialization is considered, and the mathematical relationship, particularly D₂＜D₄≤D₁-2，D₂＜D₅≤D₃2, the edge of the proximal end supporting frame 22 and the edge region of the distal end supporting frame 20 can be made to play a role of promoting endothelialization so as to enhance the long-term fixation of the supporting frame 2 at the interatrial septum target position, and the rest of the tectorial stent 2 as an implant, especially the lumbar supporting frame 21, can be effectively prevented from endothelialization, so that the lumen of the lumbar supporting frame 21 can be kept unobstructed for a long time so as to achieve the purpose of long-term shunt; further, in order to sufficiently ensure the effectiveness of the lumbar support basket 21 in preventing endothelialization, it is desirable to maximize the coverage area of the thin film a50 for preventing endothelialization, so the mathematical relationship should be further satisfied: d₂+2≤D₄And D is₂+2≤D₅(ii) a b) The film body 5 is completely attached to the support frame 2, and the folding or protruding phenomenon cannot occur in the sheath folding and releasing process of the support frame 2, so that the loading and sheath folding process is not influenced. Further, when the film body 5 is made of high polymer materials including polytetrafluoroethylene, expanded polytetrafluoroethylene, polyurethane and silica gel, the recovery of the support frame 2 can be greatly reducedThe frictional resistance of the sheath of the conveying system 31 is released or entered, thereby improving the operational smoothness, enhancing the operational experience of the operator in the operation process, and being beneficial to realizing the controllable release of the covered stent 1 in the operation and the capture recovery after the complete release; c) the film A50 and the film B51 are of an integral seamless connection structure, and the connection area of the seamless connection structure is in smooth transition so as to avoid forming thrombus and influencing a retraction sheath. For the scaffolds 2 designed to impart differential endothelialization to the membrane body 5, we observed no thrombus on the surface of the scaffold 2 6 months after implantation into the interatrial target tissue of the pig (fig. 13), but formed a large amount of neoendothelialization tissue in the proximal end part scaffold 22, especially the edge region, covered with membrane B51, while the lumen of the lumbar scaffold 21 remained open and the lumen size was comparable to the lumen diameter D of the implanted anterior lumbar scaffold 21₂The same is true, so the established target that the size of the lumen channel of the lumbar support frame 21 is effectively maintained for a long time after the tectorial stent 1 is implanted into the target tissue 6, and the stenosis or the blockage is avoided is realized, and the long-term shunting effectiveness is better compared with the similar products on the market.

In a second embodiment, the film body is a film C52, the film C52 is a flexible strip, is made of the same material as the film B51, and has the same pore diameter; the film C52 is wrapped around the support bar 210 of the support frame 2 and covers the support frame 2 completely, as shown in fig. 6. In this embodiment, the thin film body 5 is wound by a single flexible round wire or flat wire and covers all the support rods 210 of the support frame 2. The advantage of winding the single flexible round wire or flat wire is that the knotting times of the film body 5 and the support frame 2 are reduced to the greatest extent, the number of knotting heads is reduced, the increase of the whole reeling and releasing resistance of the covered stent 2 due to the excessive knotting heads is avoided, the manufacturing process is simplified to a certain extent, and the production efficiency is improved.

Preferably, a connecting hole 212 is formed at an edge node of the supporting rod 210, and the film C52 can pass through the connecting hole 212, wrap around the supporting rod 210 in a winding manner, and completely cover the supporting frame 2. This design has the following advantages: a) the connecting hole 212 can fix the film C52, so as to enhance the effectiveness and firmness of connection, ensure that the film body 5 keeps a predetermined winding form on the support frame 2, and avoid the slippage of the film C52 on the support rod 210 in the process of entering and exiting a sheath; b) the film C52 completely covers the support frame 2, so that the surface area of the metal in the covered stent 1 which is directly contacted with blood is reduced, and the risk of complications such as thrombosis and the like on the surface of the covered stent 1 is also reduced; c) the film C52 is preferably made of a material with a lower friction coefficient than the support frame 2, such as expanded polytetrafluoroethylene, so that the friction resistance of the covered stent 1 in and out of the conveying system 31 in the installation or release process can be reduced, the operation hand feeling is improved, and the installation and release controllability is ensured.

In a third embodiment, the thin film body 5 can be made of a biocompatible thin film D53, such as a biocompatible material like parylene, titanium nitride, mucopolysaccharidic sulfate, etc., and the covered stent graft 2 is covered by a coating or magnetron sputtering method, as shown in FIG. 7. The thickness of the film D53 is 1-100 μm, which can effectively enhance the adhesive force of the film D53 on the surface of the metal material, and can carry out surface modification on the metal material implanted into the human body for a long time to improve the corrosion resistance and biocompatibility of the metal material. In addition to this, this embodiment has the following advantages: a) the film D53 can prevent the inner surface of the lumen of the lumbar support basket 21 from endothelializing, so that the lumen of the lumbar support basket 21 is kept open for a long time; b) reducing the risk of potential thrombus formation on the surface of the stent graft.

In this embodiment, the edge of the support rod 210 of the proximal end support frame 22 and/or the distal end support frame 20 of the stent graft 2 is provided with a buffer structure 23, the buffer structure 23 is on the same surface as the edge area of the support rod 210 of the distal end support frame 20 and/or the proximal end support frame 22, and the buffer structure 23 is completely covered in the film B51, so as to reduce the damage of the edge of the support rod 210 to the tissue and avoid the delamination or peeling between the distal end of the support rod 210 and the film body 5.

In one embodiment, the buffer structure 23 includes a buffer structure free portion 231 and a buffer structure connecting portion 230, so that the buffer structure 23 is elastically deformed. The buffer structure 23 and the support rod 210 of the distal end support frame 20 are an integrated structure formed by laser engraving and heat setting shape memory alloy, that is: the far end of the buffer structure connecting part 230 is located on the edge of the support rod 210 on the far end support frame 20, the near end of the buffer structure free part 231 is connected with the near end of the buffer structure connecting part 230, and the far end of the buffer structure free part 231 is in a free state.

The whole buffer structure 23 is a "J" or "S" or "match" shaped structure, as shown in fig. 8a to 8c, the buffer structure 23 is on the same surface with the edge area of the support rod 210 of the distal support frame 20 or the proximal support frame 22; preferably, the rod width of the buffer structure 23 is 1/3-3/4 of the rod width of the support rod 210 on the distal support frame 20, and the cross-sectional area of the whole buffer structure 23 is no more than 3/4 of the cross-sectional area of the edge of the support rod 210 on the distal support frame 20, so that the buffer structure 23 has certain flexibility. In addition, the buffer structure 23 has the following advantages: a) the process is simple, and the preparation efficiency is high; b) the flexibility of the edges of the distal scaffold 20 can be increased to avoid damaging the atrial septal target tissue.

In a second embodiment, the cushion structure 23 is a wrapping head covering and/or wrapping the edges of the struts 210 on the distal end support strut 20 and/or the proximal end support strut 22, as shown in fig. 8 d. The wrapping head is flexible or elastic, and is made of high polymer materials such as polyurethane, polytetrafluoroethylene, expanded polytetrafluoroethylene, silica gel and the like. Preferably, a clamping groove structure 201 is arranged at the edge of the support rod 210 of the distal end support frame 20 and/or the support rod 210 of the proximal end support frame 22, and the clamping groove structure 201 can prevent the wrapping head from sliding relatively at the edge of the support rod 210 of the distal end support frame 20 and/or the support rod 210 of the proximal end support frame 22, so as to affect the buffering effect. The cushioning structure 23 of this embodiment can also serve to increase the flexibility of the edges of the struts 210 on the distal end support struts 20 and/or the struts 210 on the proximal end support struts 22 to avoid damaging the atrial septal target tissue.

In the third embodiment, the buffer structure 23 is composed of a plurality of buffer rods 232, and the number of the buffer rods 232 is even. The near ends of every two adjacent buffer rods 232 are connected with the edge of the support rod 210 on the support frame 20 at the far end part, and every two adjacent buffer rods 232 are fixedly connected at the far end and are gathered at a buffer connecting part; buffering connecting piece is the convex structure, the convex structure can prevent to be the winding form parcel and be in on the buffer beam 232 film C52, under the effect of external force, for buffer beam 232 produces and slides.

The proximal region of the bumper bar 232 is provided with an adaptive structure 30000, as shown in fig. 8 e. The adaptive structure 30000 is anatomically morphology adaptive; the adaptive structure 30000 faces radially outwards from the edge of the support frame 20 at the distal end part, and then extends in a direction away from the support frame 2 in a curved shape on a plane alpha, and the bending angle theta of the adaptive structure 30000 satisfies: theta is more than or equal to 10 degrees and less than or equal to 135 degrees; wherein the bending angle θ is defined as an angle formed between a radially outward direction of an edge surface of the distal support shelf 20 and an inward direction of a tangent line of the proximal end of the buffer rod 232. In a natural unconstrained state, the buffer structure 23 faces radially outward, has anatomical morphology adaptability, and can be attached to the target tissue 6 without damage, thereby avoiding or reducing damage to the atrial septal target tissue.

Preferably, the buffer structure 23 and the support frame 2 are an integrated structure formed by laser engraving and heat setting the same shape memory alloy tube, and the width of the buffer rod 232 is 1/3-2/3 of the width of the support rod 210 on the support frame 20 at the distal end part. The adaptive structure 30000 is located radially outward from the edge of the distal end support frame 20, then it is curved to extend obliquely across the edge of the distal end support frame 20 towards the center of the support frame 2, and the distal end of the adaptive structure 30000 is located outside the area covered by the lumbar support frame 21, as shown in fig. 8 f. This design has the following advantages:

a) the edges of the support rods 210 on the buffer structure 23 and the distal end support frame 20 are both in contact with the target tissue 6, which greatly increases the contact area, minimizes the irritation and damage of the support frame 2 to the target tissue 6, and avoids the prior art that the edges of the support rods 210 on the distal end support frame 20 are in contact with the tissue in a relatively sharp and sharp form, and further causes irritation and inflammatory reaction to the tissue and physical damage to the tissue due to stress concentration and other mechanisms;

b) the buffer structure 23 is located in the area covered by the distal end support frame 20, and has no influence on the diameter size of the distal end support frame 20; in addition, the support frame also has the characteristic of being attached to the outer surface of the far-end part support frame 20 and not being abrupt relative to the far-end part support frame 20, so that the occupied space in the left atrium is reduced, and the influence on the hemodynamics is greatly reduced. At the same time, the probability of thrombosis on the scaffold 2 is reduced;

c) the buffer structure 23 has a much smaller cross-sectional area and a much higher elastic deformation relative to all the support rods 210 at the edge area of the support frame 20 at the far end part, wherein the cross-sectional area of the buffer structure 23 is not more than half of that of all the support rods 210, so that the buffer structure 23 not only has a certain degree of radial expansion and contraction adjusting function, but also can adapt to a smaller surface area of the atrial septum, especially the area on the surface of the left atrium at the atrial septum, and the adaptability of the covered stent is greatly expanded, especially Asian people and minors; of course, the effects on the tissues adjacent to the interatrial septum, such as the mitral valve, pulmonary veins, can also be minimized or controlled; the buffer structure 23 is also made to have a certain degree of elastic deformability in the axial direction, so that the buffer structure can adapt to uneven tissues possibly existing in the left atrial region of the interatrial septum, the tissue fitting performance is remarkably improved, and the stimulation and damage of the covered stent 1 to the target tissue 6 are reduced, so that the buffer structure has wide anatomical form adaptability;

d) in the prior art, during the process of gradually expanding the distal end part support frame 20 from the release sheath, or during the process of pulling back the distal end part support frame 20 which is fully expanded from the release sheath to abut against the left atrial side of the interatrial septum tissue, due to improper operation of an operator, the delivery system is withdrawn by mistake, so that the covered stent 2, especially the distal end part support frame 20, slides down from the left atrial cavity to the right atrial cavity through the puncture hole on the interatrial septum tissue. In the present invention, the cushion structure 23 is disposed on the distal end portion supporting frame 20, especially as the cushion structure 23 of the adaptive structure 30000, since the adaptive structure 30000 is located at the distal end of the distal end portion supporting frame 20, and extends in a curved shape obliquely across the edge of the distal end portion supporting frame 20 towards the proximal direction and towards the center of the supporting frame 2, in the process that the distal end portion supporting frame 20 is gradually unfolded from the releasing sheath or in the process that the distal end portion supporting frame 20 which is sufficiently unfolded from the releasing sheath is pulled back and attached to the left atrial side of the interatrial septum tissue, when the covered stent 2 may slide off due to improper operation of an operator, the adaptive structure 30000 can always be clamped on the left atrial side of the interatrial septum target tissue, thereby forming a self-locking structure, which can prevent the covered stent 2 from further sliding off, this also means that the adaptive structure 30000 and some or all of the distal end scaffold 20 are always in the left atrial chamber event, rather than the stent graft 2 sliding completely into the right atrial chamber, thereby avoiding the above-mentioned disadvantages; therefore, the position of the covered stent 2 can be adjusted for the second time by the operator through subsequent observation images, the atrial septal pore-creating operation can be smoothly carried out, and the covered stent 2 can be safely implanted into the target position.

Further, when the film body 5 is the first embodiment, for the first buffer structure 23, the spacing structure 233 should be disposed in the gap region between the buffer structure 23 and the edge of the supporting rod 232 framework, the spacing structure 233 is disposed on the film B51, preferably, the spacing structure 233 is in the shape of a slit, and divides the film B51 into two parts capable of moving relative to each other, so as to avoid the buffer structure connecting part 230, the buffer structure free part 231, and the gap between the buffer structure connecting part 230 and the buffer structure free part 231 from being covered by the film B51, so that the buffer structure free part 231 is no longer in a bound state, and further ensure that the distal end part of the buffer structure 23, i.e. the buffer structure free part 231, can be elastically deformed relative to the edge of the supporting frame 2, and the buffer structure 23 cooperates with the spacing structure 233, the buffer structure 23 can play the function of reducing the damage of the edge of the support rod 210 to the tissue.

Example three:

based on the second embodiment, the third embodiment is different from the second embodiment in that: the edge of the proximal end part support frame 22 and/or the distal end part support frame 20 of the covered stent 1 is provided with a reinforcing structure 24, the reinforcing structure 24 can be composed of one or more reinforcing rods 240, and the reinforcing structure 24 is fixedly connected with the edge of the support frame 2 and completely covers the thin film body 5, so that the phenomenon that the thin film body 5 is folded or collapsed after the covered stent 1 is sheathed for multiple times is avoided, the endothelialization of the covered stent 1 is accelerated, the long-term fixing safety is enhanced, the attaching force of the edge area of the distal end part support frame 20 on the target tissue 6 can be enhanced, and the support frame 2 is prevented from shaking or falling off in the releasing process or after the releasing process.

In one embodiment, the reinforcing structure 24 is composed of a plurality of reinforcing rods 240, and the reinforcing rods 240 and the supporting frame 2 are an integrated structure formed by laser engraving and heat setting the same shape memory alloy tube, as shown in fig. 9 a. This design has the following advantages: a) the process is simple and the manufacture is convenient; b) the reinforcing structure 24 can improve the roundness of the edges of the proximal end struts 22 and/or the distal end struts 20 of the stent graft 1; c) the phenomenon that the film B51 covering the edge area of the distal end supporting frame 20 and/or the edge area of the proximal end supporting frame 22 is folded or collapsed after the covered stent graft 1 is withdrawn and released for multiple times is avoided, so that the film B51 together with the supporting rods 210 of the distal end supporting frame 20 and/or the supporting rods 210 of the proximal end supporting frame 22 are fully contacted with atrial septal tissue, the endothelialization of the proximal end supporting frame 22 is accelerated, and the long-term fixing safety of the covered stent graft 1 is improved.

Further preferably, the length of the reinforcing rod 240 satisfies: l is₃+L₄＝L₅+L₆And the distal node of the reinforcing structure 24 is radially connected with the node of the support rod 210 on the distal end support frame 20 to form a connecting rod structure, so that the smoothness of the covered stent 1 in the sheath is enhanced.

In another embodiment, the reinforcing structure 24 and the supporting frame 2 are combined, the reinforcing structure 24 is made of a reinforcing rod 240 made of the same shape memory alloy wire, the shape memory alloy wire sequentially passes through all the through holes arranged at the edge nodes of the supporting rods 210 on the supporting frame 20 at the distal end part to form a non-closed annular wavy structure, two ends of the shape memory alloy wire respectively pass through two side walls of the last through hole, and after being fixedly connected with the corresponding side walls, the shape memory alloy wire extends along the corresponding supporting rods 210 towards the center in a bent shape. Preferably, a flexible sheet-shaped film C52 is wrapped around the contact area between the reinforcing rod 240 and the supporting rod 210, which not only can enhance the adhesion between the two ends of the reinforcing rod 240 and the supporting rod 210, but also can prevent the two ends of the reinforcing rod 240 from tilting and piercing the film body 5 on the supporting frame 2; but also can enhance the fit of the two ends of the reinforcing rod 240 with the supporting rod 210 and the thin film body 5, so that the reinforcing rod 240 can be completely covered in the thin film body 5.

Preferably, the reinforcing rod 240 is fixedly connected with the side wall of each through hole, and the reinforcing rod 240 does not slide relative to the through hole, as shown in fig. 9b, this design can enhance the fixing effect of the reinforcing rod 240 and the edge of the supporting frame 2, and after the stent graft 1 is taken in and taken out for a plurality of times, the reinforcing rod 240 is prevented from sliding relative to the supporting frame 2 and the thin film body 5, which may cause abrasion or laceration of the thin film body 5.

Example four：

Based on the second embodiment, the fourth embodiment is different from the second embodiment in that: the covered stent 1 also comprises an anchoring structure 25, wherein the anchoring structure 25 can generate reversible elastic deformation, has form adaptivity and realizes non-invasive anchoring with target tissues; the anchoring structure 25 comprises an anchoring structure free portion 251 and an anchoring structure connecting portion 252, the anchoring structure connecting portion 252 is located on the supporting rod 210 for fixedly connecting the supporting rod 210 and the anchoring structure 25; the anchoring structure free portion 251 protrudes from the outer surface of the support rod 210 in a natural unconstrained state; the aspect ratio of the anchoring structure free portion 251 is between 2 and 50.

The anchoring structure 25 can be reversibly elastically deformed, has form adaptivity, and can realize non-invasive anchoring with target tissues.

In one embodiment, the support rod 210 on the inner side (i.e. the side contacting the target tissue) of the distal end support frame 20 is provided with an anchoring structure 25, and the anchoring structure 25 and the support frame 2 are an integrated structure formed by laser engraving and heat setting the same shape memory alloy tube, as shown in fig. 10. The anchoring structure 25 includes an anchoring structure free portion 251 and an anchoring structure connecting portion 252, the connecting portion 252 is located on the supporting rod, the anchoring structure free portion 251 protrudes from the outer surface of the supporting rod 210, and the aspect ratio of the anchoring structure free portion 251 is 2-50. Wherein the anchoring structure 25 has the following features:

a) the anchoring device can generate reversible elastic deformation, has form adaptability, and can realize non-invasive anchoring with target tissues;

b) after the covered stent 1 is held by pressing, the direction of the anchoring structure 25 is consistent with the direction of the retracting sheath, so that resistance is not generated or is very small in the process of retracting the sheath, and the sheath retracting process of the covered stent 1 is not influenced;

c) during the release of the stent graft 1, the anchoring structure 25 on the distal scaffold 20 can be anchored in the target tissue on the distal side under the action of the withdrawing force, so as to achieve the anchoring effect, so that the stent graft 1 can be safely released to the target position, and is prevented from being ejected to other positions such as the left atrium or the aorta due to incomplete release.

After the sheath is placed in the target position, the proximal end scaffold 22 is slowly pushed out of the sheath and gradually deployed. Slowly withdrawing the sheath handle proximally, slowly placing the deployed distal end support 20 on the left atrial side of the interatrial septum and engaging the target tissue. The anchoring structure 25 is hung and elastically fixed on the atrial septal tissue at the left atrial side under the action of withdrawing force, so that the anchoring effect is achieved, on one hand, the covered stent 1 can be safely released to the atrial septal target position, and the situation that the covered stent is incompletely released and is ejected to the left atrium or other places such as the aorta is avoided; on the other hand, the impact of the stent graft 1 on the target tissue can be reduced. In addition, since the anchoring structures 25 are thin and small, the trauma to the atrial septum target tissue is small.

In one embodiment, the anchoring structures 25 (shown in fig. 11) are disposed on the inner sides of the support rods 210 on the distal end portion support frame 20 and the inner sides of the support rods on the proximal end portion support frame, and the directions of the anchoring structures 25 are consistent with the direction of the sheath receiving tube. This design has the following advantages:

a) when the anchoring structure 25 is retracted into the sheath, the direction of the anchoring structure is consistent with the direction of the covered stent 1 for retracting into the sheath, and under the condition that the size of the lumen of the sheath is proper, the frictional resistance cannot be increased to influence the sheath retracting process of the support frame 2;

b) the deployment of the proximal end scaffold 22 is slow, continuous and controllable; in this process, the proximal end supporting frame 22 is completely unfolded and attached to the target tissue, and the anchoring structure 25 can be anchored to the target tissue on the right atrial side of the atrial septum under the action of the resilience force of the proximal end supporting frame 22, so as to enhance the fixing effect of the stent graft 1 on the target tissue, and avoid the phenomenon of shaking or dropping out of the target tissue under the condition of incomplete release.

The embodiments of the present invention have been described in detail, but the embodiments are merely examples, and the present invention is not limited to the embodiments described above. Any equivalent modifications and substitutions to those skilled in the art are also within the scope of the present invention. Accordingly, equivalent changes and modifications made without departing from the spirit and scope of the present invention should be covered by the present invention.

Claims

1. The utility model provides a novel tectorial membrane support, includes the support frame and the film body, the support frame is wavy or network structure that many elastic support poles enclose, the support frame is by near and including near end portion support frame, waist support frame and distal end portion support frame far away, the whole cavity tubulose that is of waist support frame, its characterized in that: the film body at least comprises a film A and a film B, the film A is of a microporous structure or a nonporous structure, the pore diameter or node distance of the film A is not more than 60 mu m, and the film A at least covers the inner surfaces of all supporting rods of the lumbar support frame, wherein the inner surfaces are all surfaces of the supporting rods which are in contact with fluid; the membrane B is a microporous structure, the aperture or node distance of the membrane B is larger than that of the membrane A, and the membrane B at least covers the outer surfaces of the marginal areas of all the support rods of the proximal end part support frame and/or the distal end part support frame, wherein the outer surfaces are all the surfaces of the support rods contacting with target tissues.

2. The stent graft as recited in claim 1, wherein the membrane a is a non-porous structure, covering the inner and outer surfaces of all the struts of the lumbar support basket; the membrane B is a microporous structure, the aperture or node distance of the membrane B is not more than 200 mu m, the membrane B covers the inner surface and the outer surface of the edge part or all of the support rods of the near-end part support frame and/or the far-end part support frame, and the membrane A and the membrane B are in an integrated seamless connection structure.

3. The stent graft of claim 2, wherein the pore size or nodal distance of the membrane a is at least 30 μ ι η less than the pore size or nodal distance of the membrane B, imparting a differential endothelialization function to the membrane body.

4. The stent graft as recited in claim 3, wherein the proximal end portion support frame, the lumbar support frame and the distal end portion support frame are sequentially and fixedly connected with each other by a plurality of support rods to form a three-dimensional net structure, the stent graft is rotationally symmetrical along a central axis m of the lumbar support frame, and the thin film body covers the whole surface of the stent graft, wherein the surface comprises an inner surface and an outer surface of the support frames and a blank part of the three-dimensional net structure, the thin film body is in a flexible sheet shape, and the thickness of the thin film body is between 1 μm and 200 μm; the covered stent is provided with a sheath retracting tolerance structure, the sheath retracting tolerance structure is used for compensating the length difference of the thin film body and the support frame on the central axis of a sheath tube when the covered stent retracts, the sheath retracting tolerance structure comprises a curled structure or a folded structure or a split structure which is arranged on the thin film B, the curled structure or the folded structure enables the thin film body to have 20% -50% of elongation, the split structure is positioned on the blank part of the three-dimensional net structure, the thin film bodies positioned on the two sides of the split structure are physically split, the thin film bodies on the two sides of the split structure can touch or overlap in a natural unconstrained state, and the thin film bodies on the two sides of the split structure are separated from each other in the sheath retracting process.

5. The stent graft of claim 4, wherein the edges of the support rods of the proximal end support frame and/or the distal end support frame of the stent graft are provided with buffer structures, the buffer structures are on the same surface as the edge regions of the support rods of the distal end support frame and/or the proximal end support frame, and the buffer structures are completely wrapped in the thin film body to reduce the damage of the edges of the support rods to tissues and avoid the delamination or peeling between the distal ends of the support rods and the thin film body, the thin film B is provided with a spacing structure, the spacing structure is located in a gap region between the buffer structures and the support rod framework, and the spacing structure ensures that the distal end portion of the buffer structures can be elastically deformed relative to the edges of the support frames.

6. The stent graft as claimed in claim 4, wherein the edge of the support rod of the support frame at the distal end part of the stent graft is provided with a buffer structure, and the buffer structure and the support frame are of an integrated structure formed by laser engraving and heat setting of the same shape memory alloy tube; the buffer structure is composed of an even number of buffer rods, and every two adjacent buffer rods are fixedly connected at the far end and are gathered at the connection part of the buffer structure; the near-end area of the buffer rod is provided with a self-adaptive structure; the adaptive structure has anatomical morphology adaptability, the adaptive structure is radially outward from the edge of the far-end supporting frame, then the adaptive structure is bent to obliquely cross the edge of the far-end supporting frame in the proximal direction and extend towards the center of the supporting frame, and the bending angle theta satisfies the following conditions: 90 DEG-175 DEG, or from the edge of the support frame at the distal end part to the outside and then extends in a direction away from the support frame in a curved shape on a plane alpha, and the bending angle theta satisfies: theta is more than or equal to 10 degrees and less than or equal to 135 degrees.

7. The stent graft of claim 1, wherein the stent graft comprises a reinforcing structure; the reinforcing structure is composed of a plurality of reinforcing rods; the reinforcing rod is fixedly connected with the supporting rod of the proximal end portion supporting frame and/or the supporting rod of the distal end portion supporting frame and is used for reinforcing the abutting force of the edge area of the proximal end portion supporting frame and/or the distal end portion supporting frame on the atrial septal tissue, and the supporting frame is further prevented from shaking or falling off in the releasing process or after the releasing process.

8. The stent graft of claim 1, wherein the stent graft further comprises an anchoring structure; the anchoring structure can generate reversible elastic deformation, has form adaptivity and realizes non-invasive anchoring with target tissues; the anchoring structure includes: an anchoring structure free portion and an anchoring structure connecting portion;

9. The stent graft of any one of claims 1-8, wherein the length of each strut is no greater than 20mm, and the included angle between adjacent struts is no greater than 120 °; the whole covered stent is in a hollow tubular shape or a hollow dumbbell shape, and the definition is as follows: the distance between the distal face of the stent graft and the distal face of the film A is L1, the distance between the proximal face of the stent graft and the proximal face of the film A is L2, and L1 and L2 satisfy the following mathematical relationship: l1 is more than 0 and less than or equal to 10mm, and L2 is more than 0 and less than or equal to 10 mm;

or, the whole covered stent is in a flat I shape, the edge area of the support frame at the far end part is provided with a tangent plane alpha, the tangent plane alpha is vertical to the central axis m of the covered stent, the edge area of the support frame at the near end part is provided with a tangent plane beta, the tangent plane beta is vertical to the central axis m of the covered stent, the number of the mesh layers of the mesh structure is 2-4, and the definition is as follows: the maximum outer diameter of the distal strut is D1, the inner diameter of the lumbar strut is D2, the maximum outer diameter of the proximal strut is D3, the maximum diameter of the membrane a covering the distal strut region is D4, the maximum diameter of the membrane a covering the proximal strut region is D5, wherein D1, D2, D3, D4 and D5 satisfy the following mathematical relationship: d1 is more than or equal to 15mm and less than or equal to 35mm, D2 is more than or equal to 3mm and less than or equal to 15mm, D3 is more than or equal to 15mm and less than or equal to 35mm, D2 is more than or equal to D4 and less than or equal to D1-2mm, and D2 is more than or equal to D5 and less than or equal to D3-2 mm.

10. The stent graft as recited in claim 9, wherein the membrane body further comprises a membrane C, and the membrane C is a flexible strip wrapped around the surface of the buffer structure and/or the reinforcement structure to completely wrap the entire buffer structure.