CA2055130C - Mesh composite graft - Google Patents
Mesh composite graftInfo
- Publication number
- CA2055130C CA2055130C CA002055130A CA2055130A CA2055130C CA 2055130 C CA2055130 C CA 2055130C CA 002055130 A CA002055130 A CA 002055130A CA 2055130 A CA2055130 A CA 2055130A CA 2055130 C CA2055130 C CA 2055130C
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- CA
- Canada
- Prior art keywords
- component
- strands
- mesh
- composite graft
- synthetic material
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
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- Health & Medical Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Biomedical Technology (AREA)
- Cardiology (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Vascular Medicine (AREA)
- Engineering & Computer Science (AREA)
- Pulmonology (AREA)
- Gastroenterology & Hepatology (AREA)
- Transplantation (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Prostheses (AREA)
- Materials For Medical Uses (AREA)
Abstract
A mesh composite graft including an inner component, an outer component formed from strands of durable material, such as polyethylene terephthalate, and an intermediate component made from strands of biocompatible synthetic material having a melting point less than that of the durable material from which the outer component is formed and less than that of the biocompatible synthetic material from which the inner component of the graft is formed. By heating the graft to a temperature greater than the melting point of the material from which the intermediate component is formed but less than the melting point of the outer component material and less than the melting point of the material from which the inner component is formed, the components are bound by the melted intermediate component to provide a totally porous, compliant composite graft reinforced by the outer component.
Description
205513~
PATENT
Case 900430 MESH COMPOSITE GRAFT
Background and Description of the Invention The present invention generally relates to implantable prostheses and the like and to methods for making same. More particularly, the invention relates to a graft, such as a vascular graft or AV-shunt, having a compliant porous inner component and a compliant porous load-bearing outer component, bound together by a porous intermediate component that is made of material having a melting point lower than that of the materials from which the inner and outer components are made. With the outer component bound by the intermediate component to the inner component, a porous, yet strengthened integral graft results.
Blood vessels are not straight, rigid tubes but elastic conduits made of a variety of materials and having a compliance that varies with functional considerations.
For example, the venous system functions, in part, as the blood reservoir for the body. In order to be able to respond to a larger volume of blood sent into the system because of, for example, a change in arterial blood pressure, the vessels of the venous system must be sufficiently compliant so that they can distend. The arterial system functions as the body's pressure reservoir.
In order to avoid the wide swings in the blood pressure and flow that are possible with every contraction and relaxation of the heart, yet be able to maintain sufficient blood pressure so that blood can be pushed into all regions of the body, including through the small-diameter arterioles and the microcirculatory bed, the arteries must have sufficient compliant strength to elastically expand and recoil without the marked distension of the venous system.
Conventional grafts, however, are generally made of materials and in shapes that provide a structure whose -G ~
20!~Sl~
compliance is markedly different from that of the walls of the vessel to which they may be attached. Grafts having walls less compliant than that of the host vessel walls are problematic in that conditions, such as intimal hyperplasia and stenotic narrowing, may develop. Grafts with walls having greater compliance than that of the vessel to which the graft is attached are problematic in that a portion of the graft wall may balloon - that is, develop an aneurysm -after implantation.
Other known grafts, while they may be compliant, may not necessarily be made from biocompatible materials.
The implantation of a graft made from such material may prompt a thrombogenic or immunological response with the resultant deleterious formation of microthrombi or micro-occlusions in and around the graft. Other grafts are made from generally non-porous materials, that, accordingly, do not facilitate the ingrowth of cells and tissue within the graft. The full incorporation of the graft into the surrounding host tissue is thereby frustrated. Still other conventional grafts are made from microporous textiles that require preclotting of the vessel wall with blood to prevent leakage of blood at implantation.
A demand therefore is present for an integral graft made from biocompatible materials and having a structure that has compliant strength similar to that of natural tissue but that is sufficiently porous so that the graft may become incorporated into the host tissue yet not leak blood. The present invention satisfies the demand.
The present invention includes a three component system, an inner component, an intermediate component, and an outer component. While the components may be made from materials having generally different melting points and different mechanical properties, at a minimum the inner component and outer component are made from a material or materials having a melting temperature higher than the 2~5~1~Q
material from which the intermediate component is made.
More specifically, the inner component is porous and is made from a biocompatible synthetic material, preferably a polyurethane composition made with an aromatic polycarbonate intermediate, having a melting point that is, at a minimum, in excess of the melting point of the composition from which the intermediate component is formed (further discussed below).
There are many methods by which the inner component may be made, such as the many known methods used to produce porous compliant vascular prostheses. One such method is termed phase inversion or separation which involves dissolving a urethane in a solvent, such as dimethyl acetamide (DMA), forming a coat on a mandrel - such as by dipping the mandrel into the dissolved urethane - and then immersing the urethane coating in a solution such as water by which DMA may be dissolved, but not urethane, thereby causing the urethane to bead-up and form a porous matrix.
Another method by which the inner component may be formed is termed particle elution. The method utilizes water soluble particles such as salt (NaC1, MgC12, CaCo2, etc.) polymers, such as polyvinylpyrrolidone, sugars etc.
The particles are mixed or blended into a urethane composition, and after forming a graft from the mixture such as by dip coating or extruding the particle filled plastic, the particle is eluted out with a suitable solvent.
Additional methods include replamineform, that involves the dissolution of a matrix, such as that of a sea urchin, out of the urethane with hydrochloric acid, spray techniques where filaments or beads of urethane are sprayed onto a mandrel to produce a porous vascular graft, and electrostatic deposition of urethane fibers from solution.
However, the porous vascular graft preferred in this invention is prepared according to the method detailed 2~5~13~
in U.S. Patent No. 4,475,972 to Wong. This patent is incorporated hereinto by reference. An antioxidant may be added to further prevent degradation of the fibers drawn of the material from which the inner component is made.
Regardless of the nature and method of manufacturing the porous inner component, the intermediate component is comprised of one or more layers of a biocompatible synthetic material, preferably a polyurethane material, having a melting point lower than the melting point of the material from which the inner component is formed and lower than the melting point of the material from which the outer component is made.
The outer component comprises a mesh network made of strands, fibers, beads or expanded versions of a durable material such as a composition of fluorocarbons, such as - expanded polytetrafluoroethylene ("ePTFE") - commonly termed Teflon - or stable polyesters, such as preferably polyethylene terephthalate ("PET") - commonly termed Dacron.
This material is preferably warp-knitted in a tricot or double tricot pattern and shaped in a tubular configuration.
It can also be appreciated that the outer component can be woven, braided, weft-knitted and the like with loose fibers, textured fibers and the like to provide increased compliance. With the three components in place, a composite graft according to the present invention is formed by heating the structure to a temperature at or above the melting point of the material from which the intermediate component is formed but below the melting temperature or temperatures of the material from which the outer component is formed and of the material from which the inner component is formed. In this temperature range, the intermediate component may melt without the melting of either the inner component and the outer component, thereby mechanically bonding the inner component to the outer component.
2~513~
The multi-component system of the present invention provides a number of advantages over conventional grafts. The use of a durable material, such as PET or ePTFE, from which to form the outer component is advantageous because of the known strength in the body of such material. Devices made from PET or ePTFE when implanted in the body are known to maintain their integrity for some three decades. Further advantageously, it has been found that a graft - made according to the present invention and with the use of PET material to form the outer component - has a burst strength and a tensile strength that is some two times greater than that of a conventional graft. Such strength prevents the dilation of the vessel in response to, for example, an increase in blood flow and/or pressure, creep relaxation of the urethane, biodegradation of the urethane, plasticization of the urethane, etc. Decreases in strength of PET that occur after implantation due, for example, to the absorption of water after implantation, are minimal as Dacron has a low water absorption ability.
The use of a knitted pattern according to which the durable strands of the outer component may be configured is advantageous due to the increased compliance such a pattern provides. As stated above, a durable material such as PET is recognized as a strong yet not necessarily compliant material. However, by knitting the strands from which the outer component is formed into a network, a compliant reinforcing outer component is formed. The use of such a material from which to form the outer component in the three component system of the present invention advantageously provides a strengthened, yet compliant graft.
The winding of strands of synthetic material, such as polyurethane over a mandrel to form an inner component is further advantageous because of the resultant porosity of the component. While the intermediate component may be made porous, for example, by painting synthetic material over the ~513 0 inner component and utilizing the phase inversion method or the particle elution method to form a porous matrix, preferably, the intermediate component is formed by winding strands of synthetic material, such as polyurethane over the inner component, to provide a highly porous network.
Utilizing strands of PET configured in a knitted pattern to form the outer reinforcement component further provides a porous network. Advantageously, by combining these individually porous components together in a composite graft, a totally porous integral graft results. Porosity is an advantage in medical devices, such as vascular grafts, because an open structure allows vascular fluid to infiltrate and communicate to and from the surrounding tissue and the interior of the graft and allows the ingrowth of tissue to occur within the graft. Accordingly, the device becomes better incorporated into the surrounding tissue, thereby further securing the device within the implantation site.
Uniting the three components into a single composite graft advantageously facilitates the use of the device. The graft may be implanted without the need for any assembly immediately prior to use. The graft may be also cut and/or sutured as a unit without the need for the separate cutting and/or suturing of each component. Methods for cutting the composite graft include scalpel, scissors, hot wires, shaped blades, and the like. The speed with which the graft may be implanted is a particularly distinct advantage since the device is implanted only when a patient is undergoing surgery.
The use of a polycarbonate intermediate rather than, for example, a polyether urethane to make the polyurethane material from which the inner component is preferably made is advantageous as the resultant inner component better resists degradation. The resistance to degradation is further aided by the addition of antioxidant to the material from which the inner component is formed.
It is, accordingly, an object of an aspect of the present invention to provide an improved graft.
An object of an aspect of the present invention is to provide an integral improved graft made from a composite of layers of synthetic materials.
It is an object of an aspect of the present invention to provide a graft that is totally porous thereby facilitating the incorporation of the graft into the site of implantation.
An object of an aspect of the present invention is to provide an improved graft having an outer component which strengthens the device without significantly impairing the overall compliance of the graft.
Various aspects of the invention are as follows:
A composite graft for implantation within a host, comprising:
an inner component made from a porous biocompatible synthetic material, shaped to form a generally elongated cylindrical shape having a lumen through which blood may flow;
an intermediate component made from a biocompatible synthetic material, having a melting point lower than the melting point of the biocompatible synthetic material from which said inner component is formed and the melting point of polyethylene terephthalate, said intermediate component positioned generally over an outer surface of said inner component;
said intermediate component as positioned over said inner component forming a fluid transmission unit;
an outer component made from a mesh formed from strands or matrices of durable material, said strands or matrices preformed in a generally elongated cylindrical shape having a lumen therethrough and a diameter which is approximately - 7a -equal to a diameter of an outer surface of said intermediate component, said outer component is positioned over said intermediate component; and said outer component as positioned over said f luid transmission unit is heated to a temperature less than the temperature at which the durable material from which the outer component is made melts and the temperature at which the material from which the inner component is made melts but greater than the temperature at which the material from which the intermediate component is made melts thereby melting said intermediate layer, whereby said components are secured to each other to form a totally porous mesh composite graft reinforced by said outer component.
A mesh composite graft prepared by a process comprising the steps of:
(a) winding strands of biocompatible synthetic material over a mandrel to form a cylindrically-shaped inner component having a lumen therethrough;
(b) winding strands of biocompatible synthetic material over an outer surface of said inner component to f orm an intermediate component;
(c) positioning an outer component comprising a preformed mesh of durable material over an outer surface of said intermediate component;
(d) said biocompatible synthetic material from which said intermediate component is made having a melting temperature less than the durable material from which said outer component is made and less than the biocompatible synthetic material from which said inner component is made;
(e) heating said components to a temperature greater than the temperature at which said biocompatible synthetic material from which said intermediate component is f ormed melts but less than the temperature at which said durable 2 ~ 1 313 material from which said outer component is made melts and less than the temperature at which said biocompatible synthetic material from which said inner component is made melts whereby said components are bound to each other;
(f) cooling said components whereby said components are bound to each other by said melted intermediate component to form a totally porous compliant mesh composite graft having a strengthened outer component.
A method for forming a mesh composite graft, which method comprises:
winding strands of biocompatible synthetic material to form a cylindrically shaped inner component having a lumen therethrough;
winding strands o~ biocompatible synthetic material over an outer surface of said inner component to form an intermediate component, positioning a preformed mesh made from strands of durable material over an outer sur~ace of said intermediate component to form an outer component;
said intermediate component material having a melting temperature less than the temperature at which the strands from which the outer component are formed melt and at which said biocompatible synthetic material from which said inner component is formed melts;
binding said components together by heating said components to a temperature greater than the temperature at which said strands of said intermediate component melt but less than the temperature at which said strands from which said outer component and said inner component are formed melt; and cooling said components a~ bound together to provide a compliant, totally porous mesh composite graft of said strands.
- 7c - 2 0~ 5 1 3 0 The foregoing and other objects, features and advantages of this invention will be clearly understood and explained with reference to the accompanying drawings and through a consideration of the following detailed description.
Brie Description of the Drawinqs In the course of this description, reference will be made to the attached drawings, wherein:
Figure 1 is a perspective view illustrating an embodiment of a composite vascular graft according to the present invention with an outer component of knitted durable material positioned over and bound by an intermediate component to an inner component; and Figure 2 is a cross sectional view of the composite vascular graft according to the present invention illustrated in Figure 1.
DescriDtion of the Particular Embodiments The present invention is a composite vascular graft - generally designated as 21 in Figures 1 and 2 -comprised of an inner component 31, an intermediate 20~513~
component 41, and an outer component 61. The inner component will be described first.
Inner component 31 is fabricated from a biocompatible synthetic material, preferably polyurethane, having a melting temperature that is, at a minimum, greater than the melting temperature of the material from which the intermediate component is formed. Preferably, in those embodiments in which the inner component 31 is formed from polyurethane, it is made with an aromatic polycarbonate urethane. Polycarbonate urethanes are preferred over polyether urethanes due to their superior biostability. The aromatic polycarbonate urethanes have melting points in the range of 150C to 230C. This is in contrast to some aliphatic polycarbonate urethanes that have melting points between 90C and 130C. It can also be appreciated that the inner member may be composed of non-urethane materials such as silicone rubber, polyolefins, fluoroelastomers, ePTFE, and the like. An antioxidant, such as Irganox 1010, may be added to the inner member to further prevent degradation of the strands from which the inner component is formed. The melting temperature of the material from which the inner component is preferably formed exceeds 150C.
The methods by which the inner component 31 may be fabricated include those disclosed in U.S. Patent No.
4,475,972 to Wong. According to a fabrication method taught in the Wong patent, termed "solution processing", the inner component material is dissolved in a solvent and forced out of one or more orifices to form one or more continuous fibers. The fibers are drawn directly onto a rotating mandrel. As the distributor or spinnerette reciprocates along the mandrel, non-woven strands are layered on top of each other to form porous, non-woven network of strands.
The intermediate layer 41 is formed of a biocompatible synthetic material, such as a polyolefin, a silicone thermoplastic material, etc., or preferably a ~5513û
polyurethane material having a melting temperature less than that of the materials from which the inner and outer components are formed. The intermediate layer can be drawn in the manner described in the Wong patent so that at least one fibrous layer is laid over the inner component 31 to form a porous intermediate layer. This intermediate layer can be spun from solution as described in the Wong patent or can be simply wound onto the inner layer from a spool of the biocompatible low melting point material. Alternatively, phase inversion or particle elution methods may be used to form a porous intermediate component. Examples of suitable low melting point biocompatible materials include the aliphatic polycarbonate or polyether urethanes with melting points of 90C to 130C. The resultant porous, non-woven network of strands forming the intermediate component 41, as drawn over the inner component 31 form a unit 51 which facilitates the transmission of fluid.
Mesh 61, composed of strands of durable material, such as PET or ePFTE , knitted or woven in a generally elongated cylindrical shape and whose inner surface 63 is of a diameter equal to or slightly larger than the diameter of the outer surface 45 of the intermediate component 41, is fitted over the intermediate component 41. To provide compliance to the mesh network of strands from which the outer component is formed, the strands are configured preferably in a knitted pattern. Tricot or double tricot warp knit patterns are preferred. Double tricot patterns are further advantageous because they provide greater depth to the outer component 61 and thereby facilitate the acceptance of and retention of sutures and tissue ingrowth through the graft 21. Tricot or double tricot warp patterns are further advantageous in that they are generally more interlocking than other patterns and therefore resist "running". Other acceptable patterns according to which the strands of the outer component 61 may be formed include ~513~
jersey or double jersey patterns, woven or braided and multiple layers of the above. Also, the fibers comprising the outer structure may be textured or non-textured and be of a variety of deniers.
The outer component 61 as positioned over the inner component and intermediate component is heated to a temperature equal to or greater than the temperature at which the material from which the intermediate component 41 is formed melts but less than the temperature and/or temperatures at which the material or materials from which the outer component and from which the inner component 31 is formed melts. When the inner component 31 is formed from the preferred material described above, the components are heated to a temperature less than 150C but greater than the temperature at which the material from which the intermediate component 41 is formed melts, such as 110C.
By maintaining the three components at such a temperature for a period of time, such as ten minutes, the intermediate component melts thereby securing the outer component 61 and the inner component 31 to each other. To further ensure the secure full engagement of the outer component 61 by the melted intermediate component 41, the outer component 61 may be forcefully pressed into the intermediate component 41 during the heating step such as mechanically and/or with or under pressure. After heating, the united three components are cooled thereby providing an integral mesh composite graft 21.
A mesh composite graft 21 according to the present invention is totally porous and compliant, yet advantageously includes a load bearing component, the outer component 61, which adds strength to the graft and prevents the failure of the graft even in response to greater fluid volume pressures from within, creep relaxation of the inner member and possible biodegradation effects of the inner member.
The advantageous compliance of the composite graft may be adjusted by varying the number of strands from which the inner component and the intermediate component 41 are formed. The compliance of the composite graft 21 may be adjusted also by varying the materials from which the inner component 31 and the intermediate component 41 are formed while maintaining the relationship that the intermediate component 41 must melt at a lower temperature than the materials from which the outer component and the material from which inner component 31 is formed. The compliance of the mesh composite graft 21 may be adjusted further by adjusting the angle at which the strands of the inner component 31 and/or the strands of the outer component 61 are laid down - a higher angle provides a less compliant component and thereby a less compliant graft.
The compliance may be adjusted even further by altering the knitting parameters, such as courses and wales per inch, the stitch density, the fiber denier, the number of strands per filament, the composition of the fibers and filaments such as a mixture of PET and Spandex compositions and whether the outer member is knitted, woven or braided.
The advantageous overall porosity of the graft 21 may be adjusted also in a number of ways. In addition to varying the size and number of the strands from which the inner component 31 and intermediate component 41 are formed, the strands of each component may be drawn at different angles to provide decreased pore size and resultant decreased porosity. Similarly, the porosity of the outer component 61, and thereby the porosity of the composite graft 21 may be varied by varying the size and/or number of the strands and stitch density used to make the outer component mesh.
It can also be appreciated that the outer component need not be a tube formed specifically for this purpose from materials as above but can also be made from a vascular graft preformed from a porous matrix material such as ePTFE. One such graft is manufactured by W.L. Gore and marketed as a Gore-Tex graft. The ePTFE graft may be sheathed over the previously described inner and intermediate components and heat fused into a similar composite graft described in this document. Similarly, the inner members may be a Gore-Tex graft, the intermediate component, a heat fusable thermoplastic, and the outer component, a Dacron knit.
Regardless of the configuration of the inner, intermediate and outer components of the graft, i.e. be it spun, salt eluted, phase inverted, wound with an outer PET
mesh, or in which an ePTFE configuration is utilized, the resultant composite graft 21 as formed may be implanted in vascular locations and retained in place through conventional methods, such as suturing. The preferred use of PET, knitted in a preferred tricot or double tricot pattern, from which to make the outer component 61 of the graft 21 provides a graft having a greater thickness than grafts without such a load bearing component. The outer component 61 facilitates the greater retention of the sutures within the graft.
It will be understood that the embodiments of the present invention as described are illustrative of some of the applications of the principles of the present invention.
Modifications may be made by those skilled in the art without departure from the spirit and scope of the lnventlon .
PATENT
Case 900430 MESH COMPOSITE GRAFT
Background and Description of the Invention The present invention generally relates to implantable prostheses and the like and to methods for making same. More particularly, the invention relates to a graft, such as a vascular graft or AV-shunt, having a compliant porous inner component and a compliant porous load-bearing outer component, bound together by a porous intermediate component that is made of material having a melting point lower than that of the materials from which the inner and outer components are made. With the outer component bound by the intermediate component to the inner component, a porous, yet strengthened integral graft results.
Blood vessels are not straight, rigid tubes but elastic conduits made of a variety of materials and having a compliance that varies with functional considerations.
For example, the venous system functions, in part, as the blood reservoir for the body. In order to be able to respond to a larger volume of blood sent into the system because of, for example, a change in arterial blood pressure, the vessels of the venous system must be sufficiently compliant so that they can distend. The arterial system functions as the body's pressure reservoir.
In order to avoid the wide swings in the blood pressure and flow that are possible with every contraction and relaxation of the heart, yet be able to maintain sufficient blood pressure so that blood can be pushed into all regions of the body, including through the small-diameter arterioles and the microcirculatory bed, the arteries must have sufficient compliant strength to elastically expand and recoil without the marked distension of the venous system.
Conventional grafts, however, are generally made of materials and in shapes that provide a structure whose -G ~
20!~Sl~
compliance is markedly different from that of the walls of the vessel to which they may be attached. Grafts having walls less compliant than that of the host vessel walls are problematic in that conditions, such as intimal hyperplasia and stenotic narrowing, may develop. Grafts with walls having greater compliance than that of the vessel to which the graft is attached are problematic in that a portion of the graft wall may balloon - that is, develop an aneurysm -after implantation.
Other known grafts, while they may be compliant, may not necessarily be made from biocompatible materials.
The implantation of a graft made from such material may prompt a thrombogenic or immunological response with the resultant deleterious formation of microthrombi or micro-occlusions in and around the graft. Other grafts are made from generally non-porous materials, that, accordingly, do not facilitate the ingrowth of cells and tissue within the graft. The full incorporation of the graft into the surrounding host tissue is thereby frustrated. Still other conventional grafts are made from microporous textiles that require preclotting of the vessel wall with blood to prevent leakage of blood at implantation.
A demand therefore is present for an integral graft made from biocompatible materials and having a structure that has compliant strength similar to that of natural tissue but that is sufficiently porous so that the graft may become incorporated into the host tissue yet not leak blood. The present invention satisfies the demand.
The present invention includes a three component system, an inner component, an intermediate component, and an outer component. While the components may be made from materials having generally different melting points and different mechanical properties, at a minimum the inner component and outer component are made from a material or materials having a melting temperature higher than the 2~5~1~Q
material from which the intermediate component is made.
More specifically, the inner component is porous and is made from a biocompatible synthetic material, preferably a polyurethane composition made with an aromatic polycarbonate intermediate, having a melting point that is, at a minimum, in excess of the melting point of the composition from which the intermediate component is formed (further discussed below).
There are many methods by which the inner component may be made, such as the many known methods used to produce porous compliant vascular prostheses. One such method is termed phase inversion or separation which involves dissolving a urethane in a solvent, such as dimethyl acetamide (DMA), forming a coat on a mandrel - such as by dipping the mandrel into the dissolved urethane - and then immersing the urethane coating in a solution such as water by which DMA may be dissolved, but not urethane, thereby causing the urethane to bead-up and form a porous matrix.
Another method by which the inner component may be formed is termed particle elution. The method utilizes water soluble particles such as salt (NaC1, MgC12, CaCo2, etc.) polymers, such as polyvinylpyrrolidone, sugars etc.
The particles are mixed or blended into a urethane composition, and after forming a graft from the mixture such as by dip coating or extruding the particle filled plastic, the particle is eluted out with a suitable solvent.
Additional methods include replamineform, that involves the dissolution of a matrix, such as that of a sea urchin, out of the urethane with hydrochloric acid, spray techniques where filaments or beads of urethane are sprayed onto a mandrel to produce a porous vascular graft, and electrostatic deposition of urethane fibers from solution.
However, the porous vascular graft preferred in this invention is prepared according to the method detailed 2~5~13~
in U.S. Patent No. 4,475,972 to Wong. This patent is incorporated hereinto by reference. An antioxidant may be added to further prevent degradation of the fibers drawn of the material from which the inner component is made.
Regardless of the nature and method of manufacturing the porous inner component, the intermediate component is comprised of one or more layers of a biocompatible synthetic material, preferably a polyurethane material, having a melting point lower than the melting point of the material from which the inner component is formed and lower than the melting point of the material from which the outer component is made.
The outer component comprises a mesh network made of strands, fibers, beads or expanded versions of a durable material such as a composition of fluorocarbons, such as - expanded polytetrafluoroethylene ("ePTFE") - commonly termed Teflon - or stable polyesters, such as preferably polyethylene terephthalate ("PET") - commonly termed Dacron.
This material is preferably warp-knitted in a tricot or double tricot pattern and shaped in a tubular configuration.
It can also be appreciated that the outer component can be woven, braided, weft-knitted and the like with loose fibers, textured fibers and the like to provide increased compliance. With the three components in place, a composite graft according to the present invention is formed by heating the structure to a temperature at or above the melting point of the material from which the intermediate component is formed but below the melting temperature or temperatures of the material from which the outer component is formed and of the material from which the inner component is formed. In this temperature range, the intermediate component may melt without the melting of either the inner component and the outer component, thereby mechanically bonding the inner component to the outer component.
2~513~
The multi-component system of the present invention provides a number of advantages over conventional grafts. The use of a durable material, such as PET or ePTFE, from which to form the outer component is advantageous because of the known strength in the body of such material. Devices made from PET or ePTFE when implanted in the body are known to maintain their integrity for some three decades. Further advantageously, it has been found that a graft - made according to the present invention and with the use of PET material to form the outer component - has a burst strength and a tensile strength that is some two times greater than that of a conventional graft. Such strength prevents the dilation of the vessel in response to, for example, an increase in blood flow and/or pressure, creep relaxation of the urethane, biodegradation of the urethane, plasticization of the urethane, etc. Decreases in strength of PET that occur after implantation due, for example, to the absorption of water after implantation, are minimal as Dacron has a low water absorption ability.
The use of a knitted pattern according to which the durable strands of the outer component may be configured is advantageous due to the increased compliance such a pattern provides. As stated above, a durable material such as PET is recognized as a strong yet not necessarily compliant material. However, by knitting the strands from which the outer component is formed into a network, a compliant reinforcing outer component is formed. The use of such a material from which to form the outer component in the three component system of the present invention advantageously provides a strengthened, yet compliant graft.
The winding of strands of synthetic material, such as polyurethane over a mandrel to form an inner component is further advantageous because of the resultant porosity of the component. While the intermediate component may be made porous, for example, by painting synthetic material over the ~513 0 inner component and utilizing the phase inversion method or the particle elution method to form a porous matrix, preferably, the intermediate component is formed by winding strands of synthetic material, such as polyurethane over the inner component, to provide a highly porous network.
Utilizing strands of PET configured in a knitted pattern to form the outer reinforcement component further provides a porous network. Advantageously, by combining these individually porous components together in a composite graft, a totally porous integral graft results. Porosity is an advantage in medical devices, such as vascular grafts, because an open structure allows vascular fluid to infiltrate and communicate to and from the surrounding tissue and the interior of the graft and allows the ingrowth of tissue to occur within the graft. Accordingly, the device becomes better incorporated into the surrounding tissue, thereby further securing the device within the implantation site.
Uniting the three components into a single composite graft advantageously facilitates the use of the device. The graft may be implanted without the need for any assembly immediately prior to use. The graft may be also cut and/or sutured as a unit without the need for the separate cutting and/or suturing of each component. Methods for cutting the composite graft include scalpel, scissors, hot wires, shaped blades, and the like. The speed with which the graft may be implanted is a particularly distinct advantage since the device is implanted only when a patient is undergoing surgery.
The use of a polycarbonate intermediate rather than, for example, a polyether urethane to make the polyurethane material from which the inner component is preferably made is advantageous as the resultant inner component better resists degradation. The resistance to degradation is further aided by the addition of antioxidant to the material from which the inner component is formed.
It is, accordingly, an object of an aspect of the present invention to provide an improved graft.
An object of an aspect of the present invention is to provide an integral improved graft made from a composite of layers of synthetic materials.
It is an object of an aspect of the present invention to provide a graft that is totally porous thereby facilitating the incorporation of the graft into the site of implantation.
An object of an aspect of the present invention is to provide an improved graft having an outer component which strengthens the device without significantly impairing the overall compliance of the graft.
Various aspects of the invention are as follows:
A composite graft for implantation within a host, comprising:
an inner component made from a porous biocompatible synthetic material, shaped to form a generally elongated cylindrical shape having a lumen through which blood may flow;
an intermediate component made from a biocompatible synthetic material, having a melting point lower than the melting point of the biocompatible synthetic material from which said inner component is formed and the melting point of polyethylene terephthalate, said intermediate component positioned generally over an outer surface of said inner component;
said intermediate component as positioned over said inner component forming a fluid transmission unit;
an outer component made from a mesh formed from strands or matrices of durable material, said strands or matrices preformed in a generally elongated cylindrical shape having a lumen therethrough and a diameter which is approximately - 7a -equal to a diameter of an outer surface of said intermediate component, said outer component is positioned over said intermediate component; and said outer component as positioned over said f luid transmission unit is heated to a temperature less than the temperature at which the durable material from which the outer component is made melts and the temperature at which the material from which the inner component is made melts but greater than the temperature at which the material from which the intermediate component is made melts thereby melting said intermediate layer, whereby said components are secured to each other to form a totally porous mesh composite graft reinforced by said outer component.
A mesh composite graft prepared by a process comprising the steps of:
(a) winding strands of biocompatible synthetic material over a mandrel to form a cylindrically-shaped inner component having a lumen therethrough;
(b) winding strands of biocompatible synthetic material over an outer surface of said inner component to f orm an intermediate component;
(c) positioning an outer component comprising a preformed mesh of durable material over an outer surface of said intermediate component;
(d) said biocompatible synthetic material from which said intermediate component is made having a melting temperature less than the durable material from which said outer component is made and less than the biocompatible synthetic material from which said inner component is made;
(e) heating said components to a temperature greater than the temperature at which said biocompatible synthetic material from which said intermediate component is f ormed melts but less than the temperature at which said durable 2 ~ 1 313 material from which said outer component is made melts and less than the temperature at which said biocompatible synthetic material from which said inner component is made melts whereby said components are bound to each other;
(f) cooling said components whereby said components are bound to each other by said melted intermediate component to form a totally porous compliant mesh composite graft having a strengthened outer component.
A method for forming a mesh composite graft, which method comprises:
winding strands of biocompatible synthetic material to form a cylindrically shaped inner component having a lumen therethrough;
winding strands o~ biocompatible synthetic material over an outer surface of said inner component to form an intermediate component, positioning a preformed mesh made from strands of durable material over an outer sur~ace of said intermediate component to form an outer component;
said intermediate component material having a melting temperature less than the temperature at which the strands from which the outer component are formed melt and at which said biocompatible synthetic material from which said inner component is formed melts;
binding said components together by heating said components to a temperature greater than the temperature at which said strands of said intermediate component melt but less than the temperature at which said strands from which said outer component and said inner component are formed melt; and cooling said components a~ bound together to provide a compliant, totally porous mesh composite graft of said strands.
- 7c - 2 0~ 5 1 3 0 The foregoing and other objects, features and advantages of this invention will be clearly understood and explained with reference to the accompanying drawings and through a consideration of the following detailed description.
Brie Description of the Drawinqs In the course of this description, reference will be made to the attached drawings, wherein:
Figure 1 is a perspective view illustrating an embodiment of a composite vascular graft according to the present invention with an outer component of knitted durable material positioned over and bound by an intermediate component to an inner component; and Figure 2 is a cross sectional view of the composite vascular graft according to the present invention illustrated in Figure 1.
DescriDtion of the Particular Embodiments The present invention is a composite vascular graft - generally designated as 21 in Figures 1 and 2 -comprised of an inner component 31, an intermediate 20~513~
component 41, and an outer component 61. The inner component will be described first.
Inner component 31 is fabricated from a biocompatible synthetic material, preferably polyurethane, having a melting temperature that is, at a minimum, greater than the melting temperature of the material from which the intermediate component is formed. Preferably, in those embodiments in which the inner component 31 is formed from polyurethane, it is made with an aromatic polycarbonate urethane. Polycarbonate urethanes are preferred over polyether urethanes due to their superior biostability. The aromatic polycarbonate urethanes have melting points in the range of 150C to 230C. This is in contrast to some aliphatic polycarbonate urethanes that have melting points between 90C and 130C. It can also be appreciated that the inner member may be composed of non-urethane materials such as silicone rubber, polyolefins, fluoroelastomers, ePTFE, and the like. An antioxidant, such as Irganox 1010, may be added to the inner member to further prevent degradation of the strands from which the inner component is formed. The melting temperature of the material from which the inner component is preferably formed exceeds 150C.
The methods by which the inner component 31 may be fabricated include those disclosed in U.S. Patent No.
4,475,972 to Wong. According to a fabrication method taught in the Wong patent, termed "solution processing", the inner component material is dissolved in a solvent and forced out of one or more orifices to form one or more continuous fibers. The fibers are drawn directly onto a rotating mandrel. As the distributor or spinnerette reciprocates along the mandrel, non-woven strands are layered on top of each other to form porous, non-woven network of strands.
The intermediate layer 41 is formed of a biocompatible synthetic material, such as a polyolefin, a silicone thermoplastic material, etc., or preferably a ~5513û
polyurethane material having a melting temperature less than that of the materials from which the inner and outer components are formed. The intermediate layer can be drawn in the manner described in the Wong patent so that at least one fibrous layer is laid over the inner component 31 to form a porous intermediate layer. This intermediate layer can be spun from solution as described in the Wong patent or can be simply wound onto the inner layer from a spool of the biocompatible low melting point material. Alternatively, phase inversion or particle elution methods may be used to form a porous intermediate component. Examples of suitable low melting point biocompatible materials include the aliphatic polycarbonate or polyether urethanes with melting points of 90C to 130C. The resultant porous, non-woven network of strands forming the intermediate component 41, as drawn over the inner component 31 form a unit 51 which facilitates the transmission of fluid.
Mesh 61, composed of strands of durable material, such as PET or ePFTE , knitted or woven in a generally elongated cylindrical shape and whose inner surface 63 is of a diameter equal to or slightly larger than the diameter of the outer surface 45 of the intermediate component 41, is fitted over the intermediate component 41. To provide compliance to the mesh network of strands from which the outer component is formed, the strands are configured preferably in a knitted pattern. Tricot or double tricot warp knit patterns are preferred. Double tricot patterns are further advantageous because they provide greater depth to the outer component 61 and thereby facilitate the acceptance of and retention of sutures and tissue ingrowth through the graft 21. Tricot or double tricot warp patterns are further advantageous in that they are generally more interlocking than other patterns and therefore resist "running". Other acceptable patterns according to which the strands of the outer component 61 may be formed include ~513~
jersey or double jersey patterns, woven or braided and multiple layers of the above. Also, the fibers comprising the outer structure may be textured or non-textured and be of a variety of deniers.
The outer component 61 as positioned over the inner component and intermediate component is heated to a temperature equal to or greater than the temperature at which the material from which the intermediate component 41 is formed melts but less than the temperature and/or temperatures at which the material or materials from which the outer component and from which the inner component 31 is formed melts. When the inner component 31 is formed from the preferred material described above, the components are heated to a temperature less than 150C but greater than the temperature at which the material from which the intermediate component 41 is formed melts, such as 110C.
By maintaining the three components at such a temperature for a period of time, such as ten minutes, the intermediate component melts thereby securing the outer component 61 and the inner component 31 to each other. To further ensure the secure full engagement of the outer component 61 by the melted intermediate component 41, the outer component 61 may be forcefully pressed into the intermediate component 41 during the heating step such as mechanically and/or with or under pressure. After heating, the united three components are cooled thereby providing an integral mesh composite graft 21.
A mesh composite graft 21 according to the present invention is totally porous and compliant, yet advantageously includes a load bearing component, the outer component 61, which adds strength to the graft and prevents the failure of the graft even in response to greater fluid volume pressures from within, creep relaxation of the inner member and possible biodegradation effects of the inner member.
The advantageous compliance of the composite graft may be adjusted by varying the number of strands from which the inner component and the intermediate component 41 are formed. The compliance of the composite graft 21 may be adjusted also by varying the materials from which the inner component 31 and the intermediate component 41 are formed while maintaining the relationship that the intermediate component 41 must melt at a lower temperature than the materials from which the outer component and the material from which inner component 31 is formed. The compliance of the mesh composite graft 21 may be adjusted further by adjusting the angle at which the strands of the inner component 31 and/or the strands of the outer component 61 are laid down - a higher angle provides a less compliant component and thereby a less compliant graft.
The compliance may be adjusted even further by altering the knitting parameters, such as courses and wales per inch, the stitch density, the fiber denier, the number of strands per filament, the composition of the fibers and filaments such as a mixture of PET and Spandex compositions and whether the outer member is knitted, woven or braided.
The advantageous overall porosity of the graft 21 may be adjusted also in a number of ways. In addition to varying the size and number of the strands from which the inner component 31 and intermediate component 41 are formed, the strands of each component may be drawn at different angles to provide decreased pore size and resultant decreased porosity. Similarly, the porosity of the outer component 61, and thereby the porosity of the composite graft 21 may be varied by varying the size and/or number of the strands and stitch density used to make the outer component mesh.
It can also be appreciated that the outer component need not be a tube formed specifically for this purpose from materials as above but can also be made from a vascular graft preformed from a porous matrix material such as ePTFE. One such graft is manufactured by W.L. Gore and marketed as a Gore-Tex graft. The ePTFE graft may be sheathed over the previously described inner and intermediate components and heat fused into a similar composite graft described in this document. Similarly, the inner members may be a Gore-Tex graft, the intermediate component, a heat fusable thermoplastic, and the outer component, a Dacron knit.
Regardless of the configuration of the inner, intermediate and outer components of the graft, i.e. be it spun, salt eluted, phase inverted, wound with an outer PET
mesh, or in which an ePTFE configuration is utilized, the resultant composite graft 21 as formed may be implanted in vascular locations and retained in place through conventional methods, such as suturing. The preferred use of PET, knitted in a preferred tricot or double tricot pattern, from which to make the outer component 61 of the graft 21 provides a graft having a greater thickness than grafts without such a load bearing component. The outer component 61 facilitates the greater retention of the sutures within the graft.
It will be understood that the embodiments of the present invention as described are illustrative of some of the applications of the principles of the present invention.
Modifications may be made by those skilled in the art without departure from the spirit and scope of the lnventlon .
Claims (30)
1. A composite graft for implantation within a host, comprising:
an inner component made from a porous biocompatible synthetic material, shaped to form a generally elongated cylindrical shape having a lumen through which blood may flow;
an intermediate component made from a biocompatible synthetic material, having a melting point lower than the melting point of the biocompatible synthetic material from which said inner component is formed and the melting point of polyethylene terephthalate, said intermediate component positioned generally over an outer surface of said inner component;
said intermediate component as positioned over said inner component forming a fluid transmission unit;
an outer component made from a mesh formed from strands or matrices of durable material, said strands or matrices preformed in a generally elongated cylindrical shape having a lumen therethrough and a diameter which is approximately equal to a diameter of an outer surface of said intermediate component, said outer component is positioned over said intermediate component; and said outer component as positioned over said fluid transmission unit is heated to a temperature less than the temperature at which the durable material from which the outer component is made melts and the temperature at which the material from which the inner component is made melts but greater than the temperature at which the material from which the intermediate component is made melts thereby melting said intermediate layer, whereby said components are secured to each other to form a totally porous mesh composite graft reinforced by said outer component.
an inner component made from a porous biocompatible synthetic material, shaped to form a generally elongated cylindrical shape having a lumen through which blood may flow;
an intermediate component made from a biocompatible synthetic material, having a melting point lower than the melting point of the biocompatible synthetic material from which said inner component is formed and the melting point of polyethylene terephthalate, said intermediate component positioned generally over an outer surface of said inner component;
said intermediate component as positioned over said inner component forming a fluid transmission unit;
an outer component made from a mesh formed from strands or matrices of durable material, said strands or matrices preformed in a generally elongated cylindrical shape having a lumen therethrough and a diameter which is approximately equal to a diameter of an outer surface of said intermediate component, said outer component is positioned over said intermediate component; and said outer component as positioned over said fluid transmission unit is heated to a temperature less than the temperature at which the durable material from which the outer component is made melts and the temperature at which the material from which the inner component is made melts but greater than the temperature at which the material from which the intermediate component is made melts thereby melting said intermediate layer, whereby said components are secured to each other to form a totally porous mesh composite graft reinforced by said outer component.
2. The mesh composite graft according to claim 1, wherein said biocompatible synthetic material from which said inner component is made is polyurethane.
3. The mesh composite graft according to claim 2, wherein said polyurethane is made with a polycarbonate intermediate.
4. The mesh composite graft according to claim 2, wherein said polyurethane is made with an aromatic polycarbonate urethane.
5. The mesh composite graft according to claim 1, wherein said biocompatible synthetic material from which said inner component is made is silicone rubber.
6. The mesh composite graft according to claim 1, wherein said biocompatible synthetic material from which said inner component is made is a polyolefin.
7. The mesh composite graft according to claim 1, wherein said biocompatible synthetic material from which said inner component is made is a fluoroelastomer.
8. The mesh composite graft according to claim 3, wherein said polyurethane includes an antioxidant to prevent degradation of said inner component.
9. The mesh composite graft according to claim 1, wherein said biocompatible synthetic material from which said intermediate component is made is polyurethane.
10. The mesh composite graft according to claim 9, wherein said polyurethane is an aliphatic polycarbonate.
11. The mesh composite graft according to claim 1, wherein said biocompatible synthetic material from which said intermediate component is made is a polyolefin.
12. The mesh composite graft according to claim 1, wherein said biocompatible synthetic material from which said intermediate component is made is a silicon thermoplastic material.
13. The mesh composite graft according to claim 1, wherein said outer component is further secured to said intermediate component and said inner component by pressing said outer component into said intermediate component during heating.
14. The mesh composite graft according to claim 1, wherein said mesh is formed by knitting said strands of polyethylene terephthalate.
15. The mesh composite graft according to claim 1, wherein said mesh is formed by knitting said strands of polyethylene terephthalate in a tricot pattern.
16. The mesh composite graft according to claim 1, wherein said mesh is formed by knitting said strands of polyethylene terephthalate in a double tricot pattern.
17. The mesh composite graft according to claim 2, wherein said mesh is formed from strands of expanded polytetrafluoroethylene.
18. The mesh composite graft according to claim 2, wherein said mesh is preformed from strands of polytetra-fluoroethylene.
19. The mesh composite graft according to claim 2, wherein said mesh is a preformed porous matrix of expanded polytetrafluoroethylene.
20. A mesh composite graft prepared by a process comprising the steps of:
(a) winding strands of biocompatible synthetic material over a mandrel to form a cylindrically-shaped inner component having a lumen therethrough;
(b) winding strands of biocompatible synthetic material over an outer surface of said inner component to form an intermediate component;
(c) positioning an outer component comprising a preformed mesh of durable material over an outer surface of said intermediate component;
(d) said biocompatible synthetic material from which said intermediate component is made having a melting temperature less than the durable material from which said outer component is made and less than the biocompatible synthetic material from which said inner component is made;
(e) heating said components to a temperature greater than the temperature at which said biocompatible synthetic material from which said intermediate component is formed melts but less than the temperature at which said durable material from which said outer component is made melts and less than the temperature at which said biocompatible synthetic material from which said inner component is made melts whereby said components are bound to each other;
(f) cooling said components whereby said components are bound to each other by said melted intermediate component to form a totally porous compliant mesh composite graft having a strengthened outer component.
(a) winding strands of biocompatible synthetic material over a mandrel to form a cylindrically-shaped inner component having a lumen therethrough;
(b) winding strands of biocompatible synthetic material over an outer surface of said inner component to form an intermediate component;
(c) positioning an outer component comprising a preformed mesh of durable material over an outer surface of said intermediate component;
(d) said biocompatible synthetic material from which said intermediate component is made having a melting temperature less than the durable material from which said outer component is made and less than the biocompatible synthetic material from which said inner component is made;
(e) heating said components to a temperature greater than the temperature at which said biocompatible synthetic material from which said intermediate component is formed melts but less than the temperature at which said durable material from which said outer component is made melts and less than the temperature at which said biocompatible synthetic material from which said inner component is made melts whereby said components are bound to each other;
(f) cooling said components whereby said components are bound to each other by said melted intermediate component to form a totally porous compliant mesh composite graft having a strengthened outer component.
21. The mesh composite graft prepared by the process according to claim 20, including the step of pressing said outer component into said intermediate component during the heating step.
22. The mesh composite graft prepared by the process according to claim 20, including the step of drying the intermediate component as wound over said inner component prior to the heating of said components.
23. A method for forming a mesh composite graft, which method comprises:
winding strands of biocompatible synthetic material to form a cylindrically shaped inner component having a lumen therethrough;
winding strands of biocompatible synthetic material over an outer surface of said inner component to form an intermediate component, positioning a preformed mesh made from strands of durable material over an outer surface of said intermediate component to form an outer component;
said intermediate component material having a melting temperature less than the temperature at which the strands from which the outer component are formed melt and at which said biocompatible synthetic material from which said inner component is formed melts;
binding said components together by heating said components to a temperature greater than the temperature at which said strands of said intermediate component melt but less than the temperature at which said strands from which said outer component and said inner component are formed melt; and cooling said components as bound together to provide a compliant, totally porous mesh composite graft of said strands.
winding strands of biocompatible synthetic material to form a cylindrically shaped inner component having a lumen therethrough;
winding strands of biocompatible synthetic material over an outer surface of said inner component to form an intermediate component, positioning a preformed mesh made from strands of durable material over an outer surface of said intermediate component to form an outer component;
said intermediate component material having a melting temperature less than the temperature at which the strands from which the outer component are formed melt and at which said biocompatible synthetic material from which said inner component is formed melts;
binding said components together by heating said components to a temperature greater than the temperature at which said strands of said intermediate component melt but less than the temperature at which said strands from which said outer component and said inner component are formed melt; and cooling said components as bound together to provide a compliant, totally porous mesh composite graft of said strands.
24. The method according to claim 23, wherein said winding of said strands from which said inner component is formed is carried out without interweaving said inner component strands.
25. The method according to claim 23, wherein said winding of said strands from which said intermediate component is formed is carried out without interweaving said intermediate component strands.
26. The method according to claim 23, wherein said preformed mesh of PET strands is formed by knitting said strands.
27. The method according to claim 26, wherein said PET
strands are knitted in a tricot pattern.
strands are knitted in a tricot pattern.
28. The method according to claim 26, wherein said PET
strands are knitted in a double tricot pattern.
strands are knitted in a double tricot pattern.
29. The method according to claim 23, including the steps of securing said outer component to said intermediate component and said inner component by pressing said outer component into said intermediate component.
30. The method according to claim 23, including the step of drying the strands from which the intermediate component are formed immediately after said winding of said intermediate component.
Applications Claiming Priority (2)
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US07/634,425 US5116360A (en) | 1990-12-27 | 1990-12-27 | Mesh composite graft |
US634,425 | 1990-12-27 |
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CA2055130A1 CA2055130A1 (en) | 1992-06-28 |
CA2055130C true CA2055130C (en) | 1995-03-07 |
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ID=24543741
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CA002055130A Expired - Fee Related CA2055130C (en) | 1990-12-27 | 1991-11-07 | Mesh composite graft |
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EP (1) | EP0492481B1 (en) |
CA (1) | CA2055130C (en) |
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Families Citing this family (280)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5242399A (en) * | 1990-04-25 | 1993-09-07 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5344426A (en) * | 1990-04-25 | 1994-09-06 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
JPH0717314Y2 (en) * | 1990-10-18 | 1995-04-26 | ソン ホーヨン | Self-expanding intravascular stent |
IE71172B1 (en) * | 1991-03-25 | 1997-01-29 | Meadow Medicals Inc | Vascular prosthesis |
WO1993006792A1 (en) | 1991-10-04 | 1993-04-15 | Scimed Life Systems, Inc. | Biodegradable drug delivery vascular stent |
US5876445A (en) * | 1991-10-09 | 1999-03-02 | Boston Scientific Corporation | Medical stents for body lumens exhibiting peristaltic motion |
US5662713A (en) * | 1991-10-09 | 1997-09-02 | Boston Scientific Corporation | Medical stents for body lumens exhibiting peristaltic motion |
CA2380683C (en) * | 1991-10-28 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Expandable stents and method for making same |
US5314446A (en) * | 1992-02-19 | 1994-05-24 | Ethicon, Inc. | Sterilized heterogeneous braids |
JPH067387A (en) * | 1992-06-26 | 1994-01-18 | Seiren Co Ltd | Artificial blood vessel and its production |
CA2146156C (en) * | 1992-10-13 | 2004-11-30 | Erik Andersen | Medical stents for body lumens exhibiting peristaltic motion |
US5716395A (en) * | 1992-12-11 | 1998-02-10 | W.L. Gore & Associates, Inc. | Prosthetic vascular graft |
US5628782A (en) * | 1992-12-11 | 1997-05-13 | W. L. Gore & Associates, Inc. | Method of making a prosthetic vascular graft |
BE1006440A3 (en) * | 1992-12-21 | 1994-08-30 | Dereume Jean Pierre Georges Em | Luminal endoprosthesis AND METHOD OF PREPARATION. |
US5441515A (en) * | 1993-04-23 | 1995-08-15 | Advanced Cardiovascular Systems, Inc. | Ratcheting stent |
US5913894A (en) * | 1994-12-05 | 1999-06-22 | Meadox Medicals, Inc. | Solid woven tubular prosthesis |
US5456667A (en) * | 1993-05-20 | 1995-10-10 | Advanced Cardiovascular Systems, Inc. | Temporary stenting catheter with one-piece expandable segment |
KR970004845Y1 (en) * | 1993-09-27 | 1997-05-21 | 주식회사 수호메디테크 | Stent for expanding a lumen |
WO1995010989A1 (en) * | 1993-10-19 | 1995-04-27 | Scimed Life Systems, Inc. | Intravascular stent pump |
US5632772A (en) * | 1993-10-21 | 1997-05-27 | Corvita Corporation | Expandable supportive branched endoluminal grafts |
US5855598A (en) * | 1993-10-21 | 1999-01-05 | Corvita Corporation | Expandable supportive branched endoluminal grafts |
US5639278A (en) * | 1993-10-21 | 1997-06-17 | Corvita Corporation | Expandable supportive bifurcated endoluminal grafts |
US5723004A (en) | 1993-10-21 | 1998-03-03 | Corvita Corporation | Expandable supportive endoluminal grafts |
DE4340755C1 (en) * | 1993-11-30 | 1995-06-29 | Zurbruegg Heinz R | Vascular prosthesis |
US5527353A (en) | 1993-12-02 | 1996-06-18 | Meadox Medicals, Inc. | Implantable tubular prosthesis |
JP2703510B2 (en) * | 1993-12-28 | 1998-01-26 | アドヴァンスド カーディオヴァスキュラー システムズ インコーポレーテッド | Expandable stent and method of manufacturing the same |
DE4414103A1 (en) * | 1994-04-22 | 1995-10-26 | Reinmueller Johannes | Molded medical implants |
US5649977A (en) * | 1994-09-22 | 1997-07-22 | Advanced Cardiovascular Systems, Inc. | Metal reinforced polymer stent |
US5741332A (en) * | 1995-01-23 | 1998-04-21 | Meadox Medicals, Inc. | Three-dimensional braided soft tissue prosthesis |
US5683449A (en) * | 1995-02-24 | 1997-11-04 | Marcade; Jean Paul | Modular bifurcated intraluminal grafts and methods for delivering and assembling same |
US5749851A (en) * | 1995-03-02 | 1998-05-12 | Scimed Life Systems, Inc. | Stent installation method using balloon catheter having stepped compliance curve |
US6264684B1 (en) | 1995-03-10 | 2001-07-24 | Impra, Inc., A Subsidiary Of C.R. Bard, Inc. | Helically supported graft |
US6451047B2 (en) | 1995-03-10 | 2002-09-17 | Impra, Inc. | Encapsulated intraluminal stent-graft and methods of making same |
US6053943A (en) * | 1995-12-08 | 2000-04-25 | Impra, Inc. | Endoluminal graft with integral structural support and method for making same |
BE1009278A3 (en) * | 1995-04-12 | 1997-01-07 | Corvita Europ | Guardian self-expandable medical device introduced in cavite body, and medical device with a stake as. |
BE1009277A3 (en) | 1995-04-12 | 1997-01-07 | Corvita Europ | Guardian self-expandable medical device introduced in cavite body, and method of preparation. |
US5700269A (en) * | 1995-06-06 | 1997-12-23 | Corvita Corporation | Endoluminal prosthesis deployment device for use with prostheses of variable length and having retraction ability |
DE69629679T3 (en) * | 1995-06-07 | 2011-07-07 | Edwards Lifesciences Corp., Calif. | REINFORCED VIDEO IMPLANT WITH AN OUTSTANDING SUPPORTED TAPE |
US5676685A (en) * | 1995-06-22 | 1997-10-14 | Razavi; Ali | Temporary stent |
US5628788A (en) * | 1995-11-07 | 1997-05-13 | Corvita Corporation | Self-expanding endoluminal stent-graft |
US6348066B1 (en) * | 1995-11-07 | 2002-02-19 | Corvita Corporation | Modular endoluminal stent-grafts and methods for their use |
US6428571B1 (en) * | 1996-01-22 | 2002-08-06 | Scimed Life Systems, Inc. | Self-sealing PTFE vascular graft and manufacturing methods |
US5800512A (en) * | 1996-01-22 | 1998-09-01 | Meadox Medicals, Inc. | PTFE vascular graft |
WO1997035533A1 (en) | 1996-03-25 | 1997-10-02 | Enrico Nicolo | Surgical mesh prosthetic material and methods of use |
CA2199890C (en) * | 1996-03-26 | 2002-02-05 | Leonard Pinchuk | Stents and stent-grafts having enhanced hoop strength and methods of making the same |
US5718159A (en) * | 1996-04-30 | 1998-02-17 | Schneider (Usa) Inc. | Process for manufacturing three-dimensional braided covered stent |
US6746425B1 (en) * | 1996-06-14 | 2004-06-08 | Futuremed Interventional | Medical balloon |
US5928279A (en) * | 1996-07-03 | 1999-07-27 | Baxter International Inc. | Stented, radially expandable, tubular PTFE grafts |
WO1998012990A1 (en) | 1996-09-26 | 1998-04-02 | Scimed Life Systems, Inc. | Support structure/membrane composite medical device |
US7749585B2 (en) * | 1996-10-08 | 2010-07-06 | Alan Zamore | Reduced profile medical balloon element |
US5824047A (en) * | 1996-10-11 | 1998-10-20 | C. R. Bard, Inc. | Vascular graft fabric |
US6036702A (en) * | 1997-04-23 | 2000-03-14 | Vascular Science Inc. | Medical grafting connectors and fasteners |
US5941908A (en) * | 1997-04-23 | 1999-08-24 | Vascular Science, Inc. | Artificial medical graft with a releasable retainer |
US5976178A (en) * | 1996-11-07 | 1999-11-02 | Vascular Science Inc. | Medical grafting methods |
US5957974A (en) * | 1997-01-23 | 1999-09-28 | Schneider (Usa) Inc | Stent graft with braided polymeric sleeve |
ATE287679T1 (en) | 1997-03-05 | 2005-02-15 | Boston Scient Ltd | COMPLIANT MULTI-LAYER STENT DEVICE |
US6019777A (en) | 1997-04-21 | 2000-02-01 | Advanced Cardiovascular Systems, Inc. | Catheter and method for a stent delivery system |
GB2324729B (en) * | 1997-04-30 | 2002-01-02 | Bradford Hospitals Nhs Trust | Lung treatment device |
US6120539A (en) | 1997-05-01 | 2000-09-19 | C. R. Bard Inc. | Prosthetic repair fabric |
CA2424551A1 (en) * | 1997-05-27 | 1998-11-27 | Schneider (Usa) Inc. | Stent and stent-graft for treating branched vessels |
US6056993A (en) * | 1997-05-30 | 2000-05-02 | Schneider (Usa) Inc. | Porous protheses and methods for making the same wherein the protheses are formed by spraying water soluble and water insoluble fibers onto a rotating mandrel |
CA2241558A1 (en) | 1997-06-24 | 1998-12-24 | Advanced Cardiovascular Systems, Inc. | Stent with reinforced struts and bimodal deployment |
US5980564A (en) * | 1997-08-01 | 1999-11-09 | Schneider (Usa) Inc. | Bioabsorbable implantable endoprosthesis with reservoir |
US6174330B1 (en) * | 1997-08-01 | 2001-01-16 | Schneider (Usa) Inc | Bioabsorbable marker having radiopaque constituents |
US6245103B1 (en) | 1997-08-01 | 2001-06-12 | Schneider (Usa) Inc | Bioabsorbable self-expanding stent |
US6340367B1 (en) * | 1997-08-01 | 2002-01-22 | Boston Scientific Scimed, Inc. | Radiopaque markers and methods of using the same |
US7753950B2 (en) | 1997-08-13 | 2010-07-13 | Advanced Cardiovascular Systems, Inc. | Stent and catheter assembly and method for treating bifurcations |
US5954766A (en) * | 1997-09-16 | 1999-09-21 | Zadno-Azizi; Gholam-Reza | Body fluid flow control device |
US5972027A (en) * | 1997-09-30 | 1999-10-26 | Scimed Life Systems, Inc | Porous stent drug delivery system |
US6371982B2 (en) | 1997-10-09 | 2002-04-16 | St. Jude Medical Cardiovascular Group, Inc. | Graft structures with compliance gradients |
US5931865A (en) * | 1997-11-24 | 1999-08-03 | Gore Enterprise Holdings, Inc. | Multiple-layered leak resistant tube |
US6626939B1 (en) * | 1997-12-18 | 2003-09-30 | Boston Scientific Scimed, Inc. | Stent-graft with bioabsorbable structural support |
US6048362A (en) * | 1998-01-12 | 2000-04-11 | St. Jude Medical Cardiovascular Group, Inc. | Fluoroscopically-visible flexible graft structures |
US6235054B1 (en) | 1998-02-27 | 2001-05-22 | St. Jude Medical Cardiovascular Group, Inc. | Grafts with suture connectors |
US6171334B1 (en) | 1998-06-17 | 2001-01-09 | Advanced Cardiovascular Systems, Inc. | Expandable stent and method of use |
US6461380B1 (en) | 1998-07-28 | 2002-10-08 | Advanced Cardiovascular Systems, Inc. | Stent configuration |
US6156064A (en) | 1998-08-14 | 2000-12-05 | Schneider (Usa) Inc | Stent-graft-membrane and method of making the same |
US7887578B2 (en) | 1998-09-05 | 2011-02-15 | Abbott Laboratories Vascular Enterprises Limited | Stent having an expandable web structure |
US6682554B2 (en) * | 1998-09-05 | 2004-01-27 | Jomed Gmbh | Methods and apparatus for a stent having an expandable web structure |
US7815763B2 (en) | 2001-09-28 | 2010-10-19 | Abbott Laboratories Vascular Enterprises Limited | Porous membranes for medical implants and methods of manufacture |
US6755856B2 (en) | 1998-09-05 | 2004-06-29 | Abbott Laboratories Vascular Enterprises Limited | Methods and apparatus for stenting comprising enhanced embolic protection, coupled with improved protection against restenosis and thrombus formation |
US20020019660A1 (en) * | 1998-09-05 | 2002-02-14 | Marc Gianotti | Methods and apparatus for a curved stent |
US6117104A (en) * | 1998-09-08 | 2000-09-12 | Advanced Cardiovascular Systems, Inc. | Stent deployment system and method of use |
US6475222B1 (en) | 1998-11-06 | 2002-11-05 | St. Jude Medical Atg, Inc. | Minimally invasive revascularization apparatus and methods |
US7044134B2 (en) * | 1999-11-08 | 2006-05-16 | Ev3 Sunnyvale, Inc | Method of implanting a device in the left atrial appendage |
US6508252B1 (en) * | 1998-11-06 | 2003-01-21 | St. Jude Medical Atg, Inc. | Medical grafting methods and apparatus |
US7128073B1 (en) | 1998-11-06 | 2006-10-31 | Ev3 Endovascular, Inc. | Method and device for left atrial appendage occlusion |
US6261255B1 (en) | 1998-11-06 | 2001-07-17 | Ronald Jay Mullis | Apparatus for vascular access for chronic hemodialysis |
US7713282B2 (en) | 1998-11-06 | 2010-05-11 | Atritech, Inc. | Detachable atrial appendage occlusion balloon |
US20040267349A1 (en) * | 2003-06-27 | 2004-12-30 | Kobi Richter | Amorphous metal alloy medical devices |
US8382821B2 (en) * | 1998-12-03 | 2013-02-26 | Medinol Ltd. | Helical hybrid stent |
US6398803B1 (en) * | 1999-02-02 | 2002-06-04 | Impra, Inc., A Subsidiary Of C.R. Bard, Inc. | Partial encapsulation of stents |
EP1161185A2 (en) | 1999-03-09 | 2001-12-12 | St. Jude Medical Cardiovascular Group, Inc. | Medical grafting methods and apparatus |
US6258124B1 (en) | 1999-05-10 | 2001-07-10 | C. R. Bard, Inc. | Prosthetic repair fabric |
US6699256B1 (en) | 1999-06-04 | 2004-03-02 | St. Jude Medical Atg, Inc. | Medical grafting apparatus and methods |
US6497650B1 (en) | 1999-07-28 | 2002-12-24 | C. R. Bard, Inc. | Hernia prosthesis |
US6540774B1 (en) | 1999-08-31 | 2003-04-01 | Advanced Cardiovascular Systems, Inc. | Stent design with end rings having enhanced strength and radiopacity |
US6319279B1 (en) | 1999-10-15 | 2001-11-20 | Edwards Lifesciences Corp. | Laminated self-sealing vascular access graft |
US6994092B2 (en) * | 1999-11-08 | 2006-02-07 | Ev3 Sunnyvale, Inc. | Device for containing embolic material in the LAA having a plurality of tissue retention structures |
US6475235B1 (en) | 1999-11-16 | 2002-11-05 | Iowa-India Investments Company, Limited | Encapsulated stent preform |
US6702849B1 (en) | 1999-12-13 | 2004-03-09 | Advanced Cardiovascular Systems, Inc. | Method of processing open-celled microcellular polymeric foams with controlled porosity for use as vascular grafts and stent covers |
US6355058B1 (en) | 1999-12-30 | 2002-03-12 | Advanced Cardiovascular Systems, Inc. | Stent with radiopaque coating consisting of particles in a binder |
US6471721B1 (en) | 1999-12-30 | 2002-10-29 | Advanced Cardiovascular Systems, Inc. | Vascular stent having increased radiopacity and method for making same |
US6537311B1 (en) | 1999-12-30 | 2003-03-25 | Advanced Cardiovascular Systems, Inc. | Stent designs for use in peripheral vessels |
US8474460B2 (en) * | 2000-03-04 | 2013-07-02 | Pulmonx Corporation | Implanted bronchial isolation devices and methods |
US6679264B1 (en) | 2000-03-04 | 2004-01-20 | Emphasys Medical, Inc. | Methods and devices for use in performing pulmonary procedures |
US20030070683A1 (en) * | 2000-03-04 | 2003-04-17 | Deem Mark E. | Methods and devices for use in performing pulmonary procedures |
US6436132B1 (en) | 2000-03-30 | 2002-08-20 | Advanced Cardiovascular Systems, Inc. | Composite intraluminal prostheses |
US7635388B1 (en) * | 2000-05-04 | 2009-12-22 | Tyler Thomas D | Device and method for incremental correction of sight disorders and occular diseases |
US6652579B1 (en) | 2000-06-22 | 2003-11-25 | Advanced Cardiovascular Systems, Inc. | Radiopaque stent |
US6821295B1 (en) * | 2000-06-26 | 2004-11-23 | Thoratec Corporation | Flared coronary artery bypass grafts |
ES2257436T3 (en) | 2000-08-23 | 2006-08-01 | Thoratec Corporation | VASCULATOR IMPLANTS COVERED AND USE PROCEDURES. |
US7404819B1 (en) | 2000-09-14 | 2008-07-29 | C.R. Bard, Inc. | Implantable prosthesis |
US6652574B1 (en) | 2000-09-28 | 2003-11-25 | Vascular Concepts Holdings Limited | Product and process for manufacturing a wire stent coated with a biocompatible fluoropolymer |
US20040030377A1 (en) * | 2001-10-19 | 2004-02-12 | Alexander Dubson | Medicated polymer-coated stent assembly |
US20070031607A1 (en) * | 2000-12-19 | 2007-02-08 | Alexander Dubson | Method and apparatus for coating medical implants |
US20020084178A1 (en) * | 2000-12-19 | 2002-07-04 | Nicast Corporation Ltd. | Method and apparatus for manufacturing polymer fiber shells via electrospinning |
WO2002074189A2 (en) * | 2001-03-20 | 2002-09-26 | Nicast Ltd. | Electrospinning nonwoven materials with rotating electrode |
US7244272B2 (en) * | 2000-12-19 | 2007-07-17 | Nicast Ltd. | Vascular prosthesis and method for production thereof |
US6641607B1 (en) | 2000-12-29 | 2003-11-04 | Advanced Cardiovascular Systems, Inc. | Double tube stent |
US6635082B1 (en) | 2000-12-29 | 2003-10-21 | Advanced Cardiovascular Systems Inc. | Radiopaque stent |
US6764504B2 (en) * | 2001-01-04 | 2004-07-20 | Scimed Life Systems, Inc. | Combined shaped balloon and stent protector |
US8277868B2 (en) * | 2001-01-05 | 2012-10-02 | Abbott Cardiovascular Systems Inc. | Balloon catheter for delivering therapeutic agents |
US20020112729A1 (en) * | 2001-02-21 | 2002-08-22 | Spiration, Inc. | Intra-bronchial obstructing device that controls biological interaction with the patient |
US6941950B2 (en) * | 2001-10-11 | 2005-09-13 | Emphasys Medical, Inc. | Bronchial flow control devices and methods of use |
US7011094B2 (en) * | 2001-03-02 | 2006-03-14 | Emphasys Medical, Inc. | Bronchial flow control devices and methods of use |
US20040074491A1 (en) * | 2001-03-02 | 2004-04-22 | Michael Hendricksen | Delivery methods and devices for implantable bronchial isolation devices |
US7798147B2 (en) * | 2001-03-02 | 2010-09-21 | Pulmonx Corporation | Bronchial flow control devices with membrane seal |
ATE303170T1 (en) * | 2001-06-11 | 2005-09-15 | Boston Scient Ltd | COMPOSITE EPTFE/TEXTIL PROSTHESIS |
US7560006B2 (en) | 2001-06-11 | 2009-07-14 | Boston Scientific Scimed, Inc. | Pressure lamination method for forming composite ePTFE/textile and ePTFE/stent/textile prostheses |
US7201940B1 (en) | 2001-06-12 | 2007-04-10 | Advanced Cardiovascular Systems, Inc. | Method and apparatus for thermal spray processing of medical devices |
US20040137066A1 (en) * | 2001-11-26 | 2004-07-15 | Swaminathan Jayaraman | Rationally designed therapeutic intravascular implant coating |
US20030050648A1 (en) * | 2001-09-11 | 2003-03-13 | Spiration, Inc. | Removable lung reduction devices, systems, and methods |
US7029490B2 (en) | 2001-09-13 | 2006-04-18 | Arthrex, Inc. | High strength suture with coating and colored trace |
DE50112209D1 (en) * | 2001-09-18 | 2007-04-26 | Abbott Lab Vascular Entpr Ltd | stent |
US6592594B2 (en) | 2001-10-25 | 2003-07-15 | Spiration, Inc. | Bronchial obstruction device deployment system and method |
US20030100944A1 (en) * | 2001-11-28 | 2003-05-29 | Olga Laksin | Vascular graft having a chemicaly bonded electrospun fibrous layer and method for making same |
US6790213B2 (en) * | 2002-01-07 | 2004-09-14 | C.R. Bard, Inc. | Implantable prosthesis |
US6929637B2 (en) * | 2002-02-21 | 2005-08-16 | Spiration, Inc. | Device and method for intra-bronchial provision of a therapeutic agent |
US20060235432A1 (en) * | 2002-02-21 | 2006-10-19 | Devore Lauri J | Intra-bronchial obstructing device that controls biological interaction with the patient |
US20030154988A1 (en) * | 2002-02-21 | 2003-08-21 | Spiration, Inc. | Intra-bronchial device that provides a medicant intra-bronchially to the patient |
WO2003075796A2 (en) * | 2002-03-08 | 2003-09-18 | Emphasys Medical, Inc. | Methods and devices for inducing collapse in lung regions fed by collateral pathways |
US20030181922A1 (en) | 2002-03-20 | 2003-09-25 | Spiration, Inc. | Removable anchored lung volume reduction devices and methods |
US20030216769A1 (en) * | 2002-05-17 | 2003-11-20 | Dillard David H. | Removable anchored lung volume reduction devices and methods |
US20030195385A1 (en) * | 2002-04-16 | 2003-10-16 | Spiration, Inc. | Removable anchored lung volume reduction devices and methods |
US20030212412A1 (en) * | 2002-05-09 | 2003-11-13 | Spiration, Inc. | Intra-bronchial obstructing device that permits mucus transport |
PT1509256E (en) | 2002-05-24 | 2009-10-15 | Angiotech Int Ag | Compositions and methods for coating medical implants |
EP1507491A1 (en) * | 2002-05-28 | 2005-02-23 | Emphasys Medical, Inc. | Implantable bronchial isolation devices and lung treatment methods |
US20040010209A1 (en) * | 2002-07-15 | 2004-01-15 | Spiration, Inc. | Device and method for measuring the diameter of an air passageway |
US20040059263A1 (en) * | 2002-09-24 | 2004-03-25 | Spiration, Inc. | Device and method for measuring the diameter of an air passageway |
ATE407629T1 (en) * | 2002-07-26 | 2008-09-15 | Emphasys Medical Inc | BRONCHIAL FLOW DEVICE WITH A MEMBRANE SEAL |
US20040082867A1 (en) * | 2002-10-29 | 2004-04-29 | Pearl Technology Holdings, Llc | Vascular graft with integrated sensor |
US7814912B2 (en) * | 2002-11-27 | 2010-10-19 | Pulmonx Corporation | Delivery methods and devices for implantable bronchial isolation devices |
WO2004049974A2 (en) | 2002-11-27 | 2004-06-17 | Emphasys Medical, Inc. | Delivery method and device for implantable bronchial isolation devices |
US6899729B1 (en) | 2002-12-18 | 2005-05-31 | Advanced Cardiovascular Systems, Inc. | Stent for treating vulnerable plaque |
US7316710B1 (en) | 2002-12-30 | 2008-01-08 | Advanced Cardiovascular Systems, Inc. | Flexible stent |
US6896697B1 (en) | 2002-12-30 | 2005-05-24 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US20040210248A1 (en) * | 2003-03-12 | 2004-10-21 | Spiration, Inc. | Apparatus, method and assembly for delivery of intra-bronchial devices |
ATE416717T1 (en) * | 2003-03-17 | 2008-12-15 | Ev3 Endovascular Inc | STENT WITH LAMINATED THIN FILM COMPOSITE |
US7100616B2 (en) * | 2003-04-08 | 2006-09-05 | Spiration, Inc. | Bronchoscopic lung volume reduction method |
US7972616B2 (en) * | 2003-04-17 | 2011-07-05 | Nanosys, Inc. | Medical device applications of nanostructured surfaces |
US20050038498A1 (en) * | 2003-04-17 | 2005-02-17 | Nanosys, Inc. | Medical device applications of nanostructured surfaces |
US7452374B2 (en) * | 2003-04-24 | 2008-11-18 | Maquet Cardiovascular, Llc | AV grafts with rapid post-operative self-sealing capabilities |
US7597704B2 (en) * | 2003-04-28 | 2009-10-06 | Atritech, Inc. | Left atrial appendage occlusion device with active expansion |
US20040230289A1 (en) * | 2003-05-15 | 2004-11-18 | Scimed Life Systems, Inc. | Sealable attachment of endovascular stent to graft |
US7200559B2 (en) * | 2003-05-29 | 2007-04-03 | Microsoft Corporation | Semantic object synchronous understanding implemented with speech application language tags |
US9039755B2 (en) | 2003-06-27 | 2015-05-26 | Medinol Ltd. | Helical hybrid stent |
US9155639B2 (en) | 2009-04-22 | 2015-10-13 | Medinol Ltd. | Helical hybrid stent |
US7533671B2 (en) | 2003-08-08 | 2009-05-19 | Spiration, Inc. | Bronchoscopic repair of air leaks in a lung |
US20050060020A1 (en) * | 2003-09-17 | 2005-03-17 | Scimed Life Systems, Inc. | Covered stent with biologically active material |
US20050123702A1 (en) * | 2003-12-03 | 2005-06-09 | Jim Beckham | Non-compliant medical balloon having a longitudinal fiber layer |
US7258697B1 (en) | 2003-12-22 | 2007-08-21 | Advanced Cardiovascular Systems, Inc. | Stent with anchors to prevent vulnerable plaque rupture during deployment |
WO2005065578A2 (en) * | 2004-01-06 | 2005-07-21 | Nicast Ltd. | Vascular prosthesis with anastomotic member |
US20050178389A1 (en) * | 2004-01-27 | 2005-08-18 | Shaw David P. | Disease indications for selective endobronchial lung region isolation |
US20050192600A1 (en) * | 2004-02-24 | 2005-09-01 | Enrico Nicolo | Inguinal hernia repair prosthetic |
US8206684B2 (en) * | 2004-02-27 | 2012-06-26 | Pulmonx Corporation | Methods and devices for blocking flow through collateral pathways in the lung |
EP2368525B1 (en) * | 2004-03-08 | 2019-09-18 | Pulmonx, Inc | Implanted bronchial isolation devices |
US8801746B1 (en) | 2004-05-04 | 2014-08-12 | Covidien Lp | System and method for delivering a left atrial appendage containment device |
US20050271844A1 (en) * | 2004-06-07 | 2005-12-08 | Scimed Life Systems, Inc. | Artificial silk reinforcement of PTCA balloon |
US7794490B2 (en) * | 2004-06-22 | 2010-09-14 | Boston Scientific Scimed, Inc. | Implantable medical devices with antimicrobial and biodegradable matrices |
US20060009839A1 (en) * | 2004-07-12 | 2006-01-12 | Scimed Life Systems, Inc. | Composite vascular graft including bioactive agent coating and biodegradable sheath |
US20060030863A1 (en) * | 2004-07-21 | 2006-02-09 | Fields Antony J | Implanted bronchial isolation device delivery devices and methods |
EP1791496B1 (en) * | 2004-08-31 | 2019-07-31 | C.R. Bard, Inc. | Self-sealing ptfe graft with kink resistance |
US7682335B2 (en) | 2004-10-15 | 2010-03-23 | Futurematrix Interventional, Inc. | Non-compliant medical balloon having an integral non-woven fabric layer |
US7309324B2 (en) * | 2004-10-15 | 2007-12-18 | Futuremed Interventional, Inc. | Non-compliant medical balloon having an integral woven fabric layer |
US7354419B2 (en) * | 2004-10-15 | 2008-04-08 | Futuremed Interventional, Inc. | Medical balloon having strengthening rods |
US20060089672A1 (en) * | 2004-10-25 | 2006-04-27 | Jonathan Martinek | Yarns containing filaments made from shape memory alloys |
US7771472B2 (en) * | 2004-11-19 | 2010-08-10 | Pulmonx Corporation | Bronchial flow control devices and methods of use |
US8029563B2 (en) * | 2004-11-29 | 2011-10-04 | Gore Enterprise Holdings, Inc. | Implantable devices with reduced needle puncture site leakage |
US7318838B2 (en) * | 2004-12-31 | 2008-01-15 | Boston Scientific Scimed, Inc. | Smart textile vascular graft |
CN101573086A (en) * | 2005-02-17 | 2009-11-04 | 尼卡斯特有限公司 | Inflatable medical device |
US8876791B2 (en) | 2005-02-25 | 2014-11-04 | Pulmonx Corporation | Collateral pathway treatment using agent entrained by aspiration flow current |
US7833263B2 (en) * | 2005-04-01 | 2010-11-16 | Boston Scientific Scimed, Inc. | Hybrid vascular graft reinforcement |
US7947207B2 (en) | 2005-04-12 | 2011-05-24 | Abbott Cardiovascular Systems Inc. | Method for retaining a vascular stent on a catheter |
US7763198B2 (en) * | 2005-04-12 | 2010-07-27 | Abbott Cardiovascular Systems Inc. | Method for retaining a vascular stent on a catheter |
AU2006259415B2 (en) * | 2005-06-15 | 2012-08-30 | Massachusetts Institute Of Technology | Amine-containing lipids and uses thereof |
JP2009501027A (en) * | 2005-06-17 | 2009-01-15 | シー・アール・バード・インコーポレイテツド | Vascular graft with kinking resistance after tightening |
US7500982B2 (en) * | 2005-06-22 | 2009-03-10 | Futurematrix Interventional, Inc. | Balloon dilation catheter having transition from coaxial lumens to non-coaxial multiple lumens |
US7544201B2 (en) * | 2005-07-05 | 2009-06-09 | Futurematrix Interventional, Inc. | Rapid exchange balloon dilation catheter having reinforced multi-lumen distal portion |
US7972359B2 (en) | 2005-09-16 | 2011-07-05 | Atritech, Inc. | Intracardiac cage and method of delivering same |
US8636794B2 (en) * | 2005-11-09 | 2014-01-28 | C. R. Bard, Inc. | Grafts and stent grafts having a radiopaque marker |
JP2009514656A (en) * | 2005-11-09 | 2009-04-09 | シー・アール・バード・インコーポレーテッド | Graft and stent graft with radiopaque beading |
US8163002B2 (en) * | 2005-11-14 | 2012-04-24 | Vascular Devices Llc | Self-sealing vascular graft |
US20070135826A1 (en) * | 2005-12-01 | 2007-06-14 | Steve Zaver | Method and apparatus for delivering an implant without bias to a left atrial appendage |
US7691151B2 (en) | 2006-03-31 | 2010-04-06 | Spiration, Inc. | Articulable Anchor |
US7829986B2 (en) * | 2006-04-01 | 2010-11-09 | Stats Chippac Ltd. | Integrated circuit package system with net spacer |
US9198749B2 (en) * | 2006-10-12 | 2015-12-01 | C. R. Bard, Inc. | Vascular grafts with multiple channels and methods for making |
US7614258B2 (en) * | 2006-10-19 | 2009-11-10 | C.R. Bard, Inc. | Prosthetic repair fabric |
US9474833B2 (en) * | 2006-12-18 | 2016-10-25 | Cook Medical Technologies Llc | Stent graft with releasable therapeutic agent and soluble coating |
US20080208325A1 (en) * | 2007-02-27 | 2008-08-28 | Boston Scientific Scimed, Inc. | Medical articles for long term implantation |
JP2008253297A (en) * | 2007-03-30 | 2008-10-23 | Univ Kansai Medical | Medical tube |
US8128679B2 (en) * | 2007-05-23 | 2012-03-06 | Abbott Laboratories Vascular Enterprises Limited | Flexible stent with torque-absorbing connectors |
US8016874B2 (en) | 2007-05-23 | 2011-09-13 | Abbott Laboratories Vascular Enterprises Limited | Flexible stent with elevated scaffolding properties |
US8216209B2 (en) | 2007-05-31 | 2012-07-10 | Abbott Cardiovascular Systems Inc. | Method and apparatus for delivering an agent to a kidney |
US9144509B2 (en) | 2007-05-31 | 2015-09-29 | Abbott Cardiovascular Systems Inc. | Method and apparatus for delivering an agent to a kidney |
US9364586B2 (en) | 2007-05-31 | 2016-06-14 | Abbott Cardiovascular Systems Inc. | Method and apparatus for improving delivery of an agent to a kidney |
US9149610B2 (en) | 2007-05-31 | 2015-10-06 | Abbott Cardiovascular Systems Inc. | Method and apparatus for improving delivery of an agent to a kidney |
US8435283B2 (en) * | 2007-06-13 | 2013-05-07 | Boston Scientific Scimed, Inc. | Anti-migration features and geometry for a shape memory polymer stent |
US8002744B2 (en) * | 2007-08-06 | 2011-08-23 | Bard Peripheral Vascular, Inc | Non-compliant medical balloon |
US8313601B2 (en) * | 2007-08-06 | 2012-11-20 | Bard Peripheral Vascular, Inc. | Non-compliant medical balloon |
US8043301B2 (en) | 2007-10-12 | 2011-10-25 | Spiration, Inc. | Valve loader method, system, and apparatus |
JP5570993B2 (en) | 2007-10-12 | 2014-08-13 | スピレーション インコーポレイテッド | Valve loader methods, systems, and apparatus |
US20090149700A1 (en) * | 2007-11-02 | 2009-06-11 | Ruben Garcia | Method and apparatus for pubic sling insertion |
US8920488B2 (en) * | 2007-12-20 | 2014-12-30 | Abbott Laboratories Vascular Enterprises Limited | Endoprosthesis having a stable architecture |
US8337544B2 (en) * | 2007-12-20 | 2012-12-25 | Abbott Laboratories Vascular Enterprises Limited | Endoprosthesis having flexible connectors |
US7850726B2 (en) * | 2007-12-20 | 2010-12-14 | Abbott Laboratories Vascular Enterprises Limited | Endoprosthesis having struts linked by foot extensions |
WO2009091899A2 (en) * | 2008-01-17 | 2009-07-23 | Boston Scientific Scimed, Inc. | Stent with anti-migration feature |
US8196279B2 (en) * | 2008-02-27 | 2012-06-12 | C. R. Bard, Inc. | Stent-graft covering process |
US9072586B2 (en) | 2008-10-03 | 2015-07-07 | C.R. Bard, Inc. | Implantable prosthesis |
EP2365962B1 (en) | 2008-11-07 | 2017-07-05 | Massachusetts Institute of Technology | Aminoalcohol lipidoids and uses thereof |
DK2198897T3 (en) * | 2008-12-19 | 2016-11-14 | Dentsply Ih Ab | PROCESS FOR THE PREPARATION OF A medical device having a crosslinked hydrophilic coating |
US8728110B2 (en) * | 2009-01-16 | 2014-05-20 | Bard Peripheral Vascular, Inc. | Balloon dilation catheter shaft having end transition |
US8814899B2 (en) * | 2009-02-23 | 2014-08-26 | Futurematrix Interventional, Inc. | Balloon catheter pressure relief valve |
US9259559B2 (en) | 2009-02-23 | 2016-02-16 | Futurematrix Interventional, Inc. | Balloon catheter pressure relief valve |
US8202301B2 (en) * | 2009-04-24 | 2012-06-19 | Warsaw Orthopedic, Inc. | Dynamic spinal rod and implantation method |
US8900215B2 (en) * | 2009-06-12 | 2014-12-02 | Bard Peripheral Vascular, Inc. | Semi-compliant medical balloon |
US9211391B2 (en) * | 2009-09-24 | 2015-12-15 | Bard Peripheral Vascular, Inc. | Balloon with variable pitch reinforcing fibers |
PT2506857T (en) | 2009-12-01 | 2018-05-14 | Translate Bio Inc | Delivery of mrna for the augmentation of proteins and enzymes in human genetic diseases |
US20110238094A1 (en) * | 2010-03-25 | 2011-09-29 | Thomas Jonathan D | Hernia Patch |
US8696738B2 (en) * | 2010-05-20 | 2014-04-15 | Maquet Cardiovascular Llc | Composite prosthesis with external polymeric support structure and methods of manufacturing the same |
EP2603168B1 (en) | 2010-08-10 | 2016-04-20 | Cook Medical Technologies LLC | Medical prostheses having bundled and non-bundled regions |
US9193827B2 (en) | 2010-08-26 | 2015-11-24 | Massachusetts Institute Of Technology | Poly(beta-amino alcohols), their preparation, and uses thereof |
US8597240B2 (en) | 2011-02-02 | 2013-12-03 | Futurematrix Interventional, Inc. | Coaxial catheter shaft having balloon attachment feature with axial fluid path |
US9238716B2 (en) | 2011-03-28 | 2016-01-19 | Massachusetts Institute Of Technology | Conjugated lipomers and uses thereof |
US8795241B2 (en) | 2011-05-13 | 2014-08-05 | Spiration, Inc. | Deployment catheter |
SI2717893T1 (en) | 2011-06-08 | 2019-10-30 | Translate Bio Inc | Lipid nanoparticle compositions and methods for mrna delivery |
EP2758010B1 (en) | 2011-09-23 | 2017-02-08 | Pulmonx, Inc | Implant loading system |
EP2770952A4 (en) * | 2011-10-25 | 2015-07-29 | Neograft Technologies Inc | Graft device with adhered fiber matrix |
EP3536787A1 (en) | 2012-06-08 | 2019-09-11 | Translate Bio, Inc. | Nuclease resistant polynucleotides and uses thereof |
KR102311614B1 (en) | 2013-03-14 | 2021-10-08 | 샤이어 휴먼 지네틱 테라피즈 인크. | Cftr mrna compositions and related methods and uses |
AU2014236396A1 (en) | 2013-03-14 | 2015-08-13 | Shire Human Genetic Therapies, Inc. | Methods for purification of messenger RNA |
US9315472B2 (en) | 2013-05-01 | 2016-04-19 | Massachusetts Institute Of Technology | 1,3,5-triazinane-2,4,6-trione derivatives and uses thereof |
CA2928078A1 (en) | 2013-10-22 | 2015-04-30 | Shire Human Genetic Therapies, Inc. | Lipid formulations for delivery of messenger rna |
CN105658242A (en) | 2013-10-22 | 2016-06-08 | 夏尔人类遗传性治疗公司 | MRNA therapy for phenylketonuria |
AU2014340092B2 (en) | 2013-10-22 | 2019-09-19 | Translate Bio, Inc. | mRNA therapy for Argininosuccinate Synthetase Deficiency |
US9814560B2 (en) | 2013-12-05 | 2017-11-14 | W. L. Gore & Associates, Inc. | Tapered implantable device and methods for making such devices |
CN110511927A (en) | 2014-04-25 | 2019-11-29 | 川斯勒佰尔公司 | The purification process of mRNA |
JP6557722B2 (en) | 2014-05-30 | 2019-08-07 | シャイアー ヒューマン ジェネティック セラピーズ インコーポレイテッド | Biodegradable lipids for delivery of nucleic acids |
CN111588695A (en) | 2014-06-24 | 2020-08-28 | 川斯勒佰尔公司 | Stereochemically enriched compositions for delivery of nucleic acids |
US9840479B2 (en) | 2014-07-02 | 2017-12-12 | Massachusetts Institute Of Technology | Polyamine-fatty acid derived lipidoids and uses thereof |
US20160175082A1 (en) * | 2014-12-23 | 2016-06-23 | Novus Scientific Ab | Resorbable medical mesh implant for repair or prevention of parastomal hernia |
CN110946684B (en) | 2015-06-05 | 2022-06-03 | W.L.戈尔及同仁股份有限公司 | Hypotonic blood volume implantable prosthesis with tapered portion |
US10130465B2 (en) | 2016-02-23 | 2018-11-20 | Abbott Cardiovascular Systems Inc. | Bifurcated tubular graft for treating tricuspid regurgitation |
MA47603A (en) | 2017-02-27 | 2020-01-01 | Translate Bio Inc | NEW ARNM CFTR WITH OPTIMIZED CODONS |
US11432809B2 (en) | 2017-04-27 | 2022-09-06 | Boston Scientific Scimed, Inc. | Occlusive medical device with fabric retention barb |
IL270631B2 (en) | 2017-05-16 | 2024-03-01 | Translate Bio Inc | Treatment of cystic fibrosis by delivery of codon-optimized mrna encoding cftr |
CN108186162A (en) * | 2017-12-06 | 2018-06-22 | 江苏百优达生命科技有限公司 | A kind of three-decker composite artificial blood vessel |
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EP3740139A1 (en) | 2018-01-19 | 2020-11-25 | Boston Scientific Scimed Inc. | Occlusive medical device with delivery system |
US10575973B2 (en) | 2018-04-11 | 2020-03-03 | Abbott Cardiovascular Systems Inc. | Intravascular stent having high fatigue performance |
WO2019213274A1 (en) | 2018-05-02 | 2019-11-07 | Boston Scientific Scimed, Inc. | Occlusive sealing sensor system |
US11241239B2 (en) | 2018-05-15 | 2022-02-08 | Boston Scientific Scimed, Inc. | Occlusive medical device with charged polymer coating |
EP3801301A1 (en) | 2018-06-08 | 2021-04-14 | Boston Scientific Scimed Inc. | Occlusive device with actuatable fixation members |
WO2019237004A1 (en) | 2018-06-08 | 2019-12-12 | Boston Scientific Scimed, Inc. | Medical device with occlusive member |
EP3817671A1 (en) | 2018-07-06 | 2021-05-12 | Boston Scientific Scimed Inc. | Occlusive medical device |
CN112714632A (en) | 2018-08-21 | 2021-04-27 | 波士顿科学医学有限公司 | Barbed protruding member for cardiovascular devices |
CN112930396A (en) | 2018-08-24 | 2021-06-08 | 川斯勒佰尔公司 | Method for purifying messenger RNA |
WO2021011694A1 (en) | 2019-07-17 | 2021-01-21 | Boston Scientific Scimed, Inc. | Left atrial appendage implant with continuous covering |
CN114340516A (en) | 2019-08-30 | 2022-04-12 | 波士顿科学医学有限公司 | Left atrial appendage implant with sealing disk |
US11903589B2 (en) | 2020-03-24 | 2024-02-20 | Boston Scientific Scimed, Inc. | Medical system for treating a left atrial appendage |
Family Cites Families (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4475972A (en) * | 1981-10-01 | 1984-10-09 | Ontario Research Foundation | Implantable material |
DE3566498D1 (en) * | 1984-03-01 | 1989-01-05 | Kanegafuchi Chemical Ind | Artificial vessel and process for preparing the same |
US4743252A (en) * | 1986-01-13 | 1988-05-10 | Corvita Corporation | Composite grafts |
US4816339A (en) * | 1987-04-28 | 1989-03-28 | Baxter International Inc. | Multi-layered poly(tetrafluoroethylene)/elastomer materials useful for in vivo implantation |
DE3830481A1 (en) * | 1988-09-08 | 1990-03-22 | Ethicon Gmbh | Tubular implant and method of producing it |
US4969896A (en) * | 1989-02-01 | 1990-11-13 | Interpore International | Vascular graft prosthesis and method of making the same |
-
1990
- 1990-12-27 US US07/634,425 patent/US5116360A/en not_active Expired - Lifetime
-
1991
- 1991-11-07 CA CA002055130A patent/CA2055130C/en not_active Expired - Fee Related
- 1991-12-19 EP EP91121876A patent/EP0492481B1/en not_active Expired - Lifetime
- 1991-12-19 DE DE69108698T patent/DE69108698T2/en not_active Expired - Lifetime
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DE69108698T2 (en) | 1996-01-11 |
DE69108698D1 (en) | 1995-05-11 |
CA2055130A1 (en) | 1992-06-28 |
EP0492481A1 (en) | 1992-07-01 |
US5116360A (en) | 1992-05-26 |
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