An aneurysm is a medical condition indicated generally by an expansion and weakening of the wall of an artery of a patient. Aneurysms can develop at various sites within a patient's body. Thoracic aortic aneurysms (TAAs) or abdominal aortic aneurysms (AAAs) are manifested by an expansion and weakening of the aorta, and are serious and life threatening conditions for which intervention is generally indicated. Existing methods of treating aortic aneurysms include invasive surgical procedures with graft replacement of the affected vessel or body lumen or reinforcement of the vessel with a graft.
Surgical procedures to treat aortic aneurysms tend to have relatively high morbidity and mortality rates due to the risk factors inherent to surgical repair of this disease. Painful recoveries involving long hospital stays are typical as well. This is especially true for surgical repair of TAAs, which is generally regarded as involving higher risk and more difficulty when compared to surgical repair of AAAs. An example of a surgical procedure involving repair of an aortic aneurysm is described in a book titled “Surgical Treatment of Aortic Aneurysms” by Denton A. Cooley, M.D., published in 1986 by W.B. Saunders Company.
Due to the inherent risks and complexities of surgical repair of aortic aneurysms, endovascular repair has become a widely-used alternative therapy, most notably in treating AAAs. Early work in this field directed towards percutaneous endovascular therapy is exemplified by Lawrence, Jr. et al. in “Percutaneous Endovascular Graft: Experimental Evaluation”, Radiology (May 1987) and by Mirich et al. in “Percutaneously Placed Endovascular Grafts for Aortic Aneurysms: Feasibility Study,” Radiology (March 1989).
Commercially available endoprostheses for the endovascular treatment of AAAs include the AneuRx™ stent graft manufactured by Medtronic, Inc. of Minneapolis, Minn., the Zenith™ stent graft system sold by Cook, Inc. of Bloomington, Ind., the PowerLink® stent-graft system manufactured by Endologix, Inc. of Irvine, Calif., and the Excluder® stent graft system manufactured by W.L. Gore & Associates, Inc. of Newark, Del. A commercially available stent graft for the treatment of TAAs is the TAG™ system manufactured by W.L. Gore & Associates, Inc.
When deploying such devices by catheter or other suitable instrument, it is advantageous to have a flexible and low profile stent graft and delivery system, particularly for patients with small vessels and/or tortuous vascular anatomies. Many of the existing devices for the endovascular treatment of aortic aneurysms, while representing significant technological advancements over previous devices, remain relatively large in transverse profile, often up to 24 French. In addition, some existing systems have greater than desired longitudinal stiffness, which can complicate the delivery process. As such, relatively non-invasive, even percutaneous, endovascular treatment of aortic aneurysms is not available for many patients that would benefit from such a procedure and can be more difficult to carry out for those patients for whom the procedure is indicated. What has been needed is a graft that can be safely and reliably deployed using a flexible low profile system.
Advantages in the treatment of fluid flow vessels of a patient's body such as ease of deployment and low profile delivery can be achieved by use of a modular endovascular graft design. In addition, advantages may be achieved by the use of modular inflatable grafts or stent grafts that include inflatable channels or cuffs, and in some embodiments, a network of inflatable channels that provide mechanical support and rigidity for the graft. Inflatable channels or cuffs may also be useful for providing a seal against an inside surface of a patient's fluid vessel and when used in combination with expandable stents which are axially separated or distinct from the cuffs or channels. The sealing function of the cuffs or channels may be separated from an anchoring or securing function of an expandable stent.
In one embodiment, the present invention provides a modular endovascular graft. The graft comprises a first graft body section that is at least partially inflatable. A second graft body section is securable to at least a portion of the first graft body section. In one configuration, both the first graft body section and the second graft body section are at least partially inflatable.
In a further embodiment, a modular endovascular graft has a first graft body section with a first fluid flow lumen bounded by a first wall portion. A first attachment element is disposed on the first wall portion and an inflatable cuff surrounds the first fluid flow lumen and extends radially from the first wall portion when in an inflated state. A second graft body section has a second fluid flow lumen bounded by a second wall portion. A second attachment element is disposed on the second wall portion which is configured to be secured to the first attachment element with the first fluid flow lumen sealed to the second fluid flow lumen.
In another embodiment, a modular endovascular graft has a first graft body section with a first fluid flow lumen bounded by a first wall portion and a first attachment element that includes a first inflatable element disposed on the first wall portion. A second graft body section has a second fluid flow lumen bounded by a second wall portion and a second attachment element disposed on the second wall portion which is configured to engage the first inflatable element when the first inflatable element is in an inflated state to prevent axial separation of the first and second graft body sections.
In another embodiment, a modular endovascular graft includes a first graft body section having a first fluid flow lumen and a first inflatable element that has a first reduced circumference shoulder portion on an inner surface of the first graft body section when the element is in an inflated state. A second graft body section has a second fluid flow lumen and is secured to the first graft body section by a second reduced circumference shoulder portion that mechanically engages the first reduced circumference shoulder portion to prevent axial separation of the first and second graft body sections.
In another embodiment, a bifurcated modular endovascular graft includes a main graft body section with a main fluid flow lumen therein, an ipsilateral port in fluid communication with the main fluid flow lumen and a contralateral port in fluid communication with the main fluid flow lumen. An ipsilateral attachment element is disposed on the main graft body section adjacent the ipsilateral port. A contralateral attachment element disposed on the main graft body section adjacent the contralateral port. An ipsilateral graft body section having an ipsilateral fluid flow lumen therein and a first attachment element disposed adjacent a proximal end of the ipsilateral graft body section is secured to the ipsilateral attachment element with the ipsilateral fluid flow lumen sealed to the main fluid flow lumen. A contralateral graft body section having a contralateral fluid flow lumen and a second attachment element disposed adjacent a proximal end of the contralateral graft body section is secured to the contralateral attachment element with the contralateral fluid flow lumen sealed to the main fluid flow lumen.
In yet another embodiment, a modular endovascular graft includes a first graft body section having a first fluid flow lumen bounded by a first wall portion, a first attachment element disposed on an outside surface of the first wall portion and a radial compression member secured to and disposed about the first graft body section at least partially over the first attachment element. The modular endovascular graft also includes a second graft body section having a second fluid flow lumen bounded by a second wall portion, a second attachment element disposed on an inside surface of the second wall portion engaged with the first attachment element with the first fluid flow lumen sealed to the second fluid flow lumen. The radial compression member applies inward radial force to the joint between the first attachment element and the second attachment element in order to enhance the strength of the joint.
In an embodiment of a method of treating a fluid flow vessel of a patient, a modular endovascular graft is provided including a first graft body section having a first fluid flow lumen and a first inflatable element that comprises a first reduced circumference shoulder portion on an inner surface of the first graft body section when the element is in an inflated state. The modular endovascular graft also includes a second graft body section having a second fluid flow lumen and is secured to the first graft body section by a second reduced circumference shoulder portion that mechanically engages the first reduced circumference shoulder portion to prevent axial separation of the first and second graft body sections. The first graft body section is deployed within a desired location of the patient's fluid flow vessel. The second graft body section is deployed adjacent the first graft body section such that the second attachment element is adjacent the first inflatable element. The first inflatable element is then inflated so as to engage the second attachment element and secure the first graft body section to the second graft body section.
These and other advantages of embodiments of the invention will become more apparent from the following detailed description of the invention when taken in conjunction with the accompanying exemplary drawings.
Embodiments of the invention are directed generally to methods and devices for treatment of fluid flow vessels with the body of a patient. Treatment of blood vessels is specifically indicated for some embodiments, and, more specifically, treatment of abdominal aortic aneurysms for others.
A contralateral attachment element 16 is disposed on a contralateral leg 16A that extends distally from the distal portion 19 of the main graft body section and has a contralateral port 17 that is in fluid communication with the main fluid flow lumen 13. The main graft body section 12, ipsilateral leg 14A and contralateral leg 16A form a bifurcated “Y” shaped configuration with the main fluid flow lumen 13 of the main graft body section 12 typically having a larger transverse dimension and area than that of either the ipsilateral port 15 or contralateral port 17. The transverse dimension or diameter of the main fluid flow lumen may be from about 15.0 mm to about 32.0 mm. The transverse dimension or diameter of the ipsilateral and contralateral ports 15 and 17 may be from about 5.0 to about 20.0 mm. The main graft body section 12 may comprise polytetrafluoroethylene (PTFE) or expanded polytetrafluoroethylene (ePTFE). In particular, main graft body section 12 may comprise any number of layers of PTFE and/or ePTFE, including from about 2 to about 15 layers, having an uncompressed layered thickness of about 0.003 inch to about 0.015 inch. Unless otherwise specifically stated, the term “PTFE” as used herein includes both PTFE and ePTFE. Furthermore, the graft body sections of the present invention described herein may comprise all PTFE, all ePTFE, or a combination thereof. Such graft body sections may comprise any alternative biocompatible materials, such as DACRON, suitable for graft applications.
Descriptions of various constructions of graft body sections may be found in commonly-owned U.S. Pat. No. 6,776,604, entitled “Method and Apparatus for Manufacturing an Endovascular Graft Section”, pending U.S. patent application Ser. No. 10/029,584, entitled “Endovascular Graft Joint and Method of Manufacture”, and pending U.S. Patent Application Ser. No. 10/029,559, entitled “Method and Apparatus for Shape Forming Endovascular Graft Material”, all of which were filed on Dec. 20, 2001 to Chobotov et al., the entirety of each of which is incorporated herein by reference.
An optional main expandable stent 18 is disposed within the main graft body section 12 and extends longitudinally within the main graft body section 12 to provide mechanical support to the graft 10. The optional main expandable stent 18 can be mechanically secured to the inside surface of the wall portion of the main graft body section 12, as shown in
A network of inflatable elements or channels 21 is disposed on the main graft body section 12 which may be inflated under pressure with an inflation material through a main fill port 20 that has a lumen disposed therein in fluid communication with the network of inflatable channels 21. The inflation material may be retained within the network of inflatable channels 21 by a one way-valve 20A (
The inflatable cuff 22 and network of inflatable channels 21 may be filled during deployment of the graft 10 with any suitable inflation material that provides outward pressure or a rigid structure from within the inflatable cuff or network of inflatable channels 21. Biocompatible gases or liquids may be used, including curable polymeric materials or gels, such as the polymeric biomaterials described in pending U.S. patent application Ser. No. 09/496,231 filed Feb. 1, 2000, and entitled “Biomaterials Formed by Nucleophilic Addition Reaction to Conjugated Unsaturated Groups” to Hubbell et al. and pending U.S. patent application Ser. No. 09/586,937, filed Jun. 2, 2000, and entitled “Conjugate Addition Reactions for Controlled Delivery of Pharmaceutically Active Compounds” to Hubbell et al. and further discussed in commonly owned pending U.S. patent application Ser. No. 10/327,711, filed Dec. 20, 2002, and entitled “Advanced Endovascular Graft” to Chobotov, et al., each of which is incorporated by reference herein in its entirety.
A proximal expandable stent 25 may be disposed proximally of the main graft body section 12 and is secured to a proximal connector ring 26 which is at least partially disposed in proximal portion 23 of the main graft body section 12. The proximal connector ring 26 has connector elements 26A extending proximally from the proximal connector ring 26 beyond the proximal end of the main graft body section 12 in order to couple or be otherwise secured to mating connector elements of the proximal expandable stent 25. The proximal expandable stent 25 may have a cylindrical or ring-like configuration with the element of the stent being preformed in a serpentine or sine wave pattern within the cylinder as shown in
The proximal expandable stent 25 may be made from a variety of resilient and expandable materials, such as stainless steel, nickel titanium alloy or the like. The proximal expandable stent 25 or additional stents secured to proximal expandable stent 25 may have the same or similar features, dimensions or materials to those of the stents described in commonly owned pending U.S. patent application Ser. No. 10/327,711. The proximal expandable stent 25 may also be secured to the connector ring 26 in the same or similar fashion as described in the incorporated application above.
A ipsilateral graft body section 27 has a ipsilateral fluid flow lumen 28 disposed therein which is bounded by a wall portion 27A of the ipsilateral graft body section 27, as shown in
As shown in
A contralateral graft body section 41 has a contralateral fluid flow lumen 42 disposed therein which is bounded by a wall portion 41A of the ipsilateral graft body section 41, as shown in
As shown in
Referring to
Circumferential inflatable channels 60 of the ipsilateral attachment element 14 are shown in an inflated state with an inflation material 60A disposed within the circumferential inflatable channels 60. The configuration of the inflated circumferential inflatable channels 60 of the ipsilateral attachment element 14 includes reduced circumference shoulder portions 63 which intrude into the ipsilateral port 15 and provide a surface for engagement of the mating reduced circumference shoulder portions 64 of the first attachment element 31 as shown.
The mechanical interference or engagement of the reduced circumference shoulder portions 63 and 64 prevent axial movement of the ipsilateral graft body section 27 in a distal direction relative to the ipsilateral attachment element 14. The mechanical interference or engagement of the reduced circumference shoulder portions 63 and 64 would also limit the axial travel of the ipsilateral graft body section 27 in a proximal direction relative to the ipsilateral attachment element 14. Reinforcing stents 34 of the first attachment element 31 of the ipsilateral graft body section 27 provide a resilient surface for seating of the circumferential inflatable channels 60 of the ipsilateral attachment 14 element, help create a seal with the channels 60 and may also prevent intrusion of the circumferential channels 60 into the ipsilateral fluid flow lumen 28.
The inflatable circumferential channels 60 also may provide a seal between the ipsilateral attachment element 14 and an outside surface of the ipsilateral graft body section 27. Likewise, the inflatable circumferential channels 33 of the ipsilateral graft body section 27 may provide a seal between the ipsilateral graft body section 27 and the ipsilateral attachment element by pressing against an inside surface of the ipsilateral port 15 of the ipsilateral attachment element 14.
The proximal portion 32 of the ipsilateral graft body section 27 may include a flared or outwardly tapered reinforced segment 65 disposed proximally of the first attachment element 31. The flared reinforced segment 65 extends to the proximal end of the ipsilateral graft body section 27 and has a flared reinforcing ring 66 that is disposed in the proximal portion 32 of the ipsilateral graft body section 27. The ring 66 will have a generally frustoconical configuration that matches the configuration of the flared reinforced segment 65 and provides a resilient outward radial force of radially compressed or restrained. The flared reinforced segment 65 can mechanically engage a tapered inside surface 67 of the main graft body section 12 to further prevent axial movement of the ipsilateral graft body section 27 in a distal direction relative to the ipsilateral attachment element 14. The flared reinforced segment 65 may also provide a smooth lumen at the transition between the main fluid flow lumen 13 and the ipsilateral fluid flow lumen 28 by providing a smooth tapered lead-in to the ipsilateral fluid flow lumen 28 from the main fluid flow lumen 13.
The joint between the contralateral attachment element 16 and the contralateral graft body section 41 may be carried out in the same or similar fashion to the joint between the ipsilateral attachment element 14 and ipsilateral graft body section 27 described above. In addition, the joint between the contralateral attachment element 16 and the contralateral graft body 41 section may have the same or similar features, such as axial length adjustability, as the joint between the ipsilateral attachment element 14 and ipsilateral graft body section 27 described above.
Referring to
In this configuration, the reduced circumference shoulder portions 63 of the ipsilateral attachment element 14 are again mechanically engaged with the reduced circumference shoulder portions 64 of the first attachment element 31. However, the engagement is shifted such that the distal most circumferential inflatable channel 33 is no longer engaging a circumferential inflatable channel 60 of the ipsilateral attachment element 14. In addition, the flared reinforced segment 65 is disposed within the ipsilateral attachment element 14 and is pressing radially outward against an inside surface of the wall portion 12A of the ipsilateral leg 14A and is also partially mechanically engaging a reduced circumference shoulder portion 68 of one of the circumferential inflatable channels 60 as shown in
Deployment of the bifurcated modular endovascular graft 10 may be carried out by any suitable method, including techniques and accompanying apparatus as disclosed in commonly owned U.S. Pat. No. 6,761,733 to Chobotov et al., pending U.S. patent application Ser. No. 10/686,863 entitled “Delivery Systems and Methods for Bifurcated Endovascular Graft” to Chobotov et al., filed Oct. 16, 2003 the entirety of both are incorporated herein by reference. In one deployment method, the main graft body section 12 is advanced in the patient's vessel 11, typically in a proximal direction from the ipsilateral iliac artery, to a desired site of deployment, such as the abdominal aorta 11 shown in
The ipsilateral graft body section 27 is then advanced into the patient's vasculature, again typically in a proximal direction from the ipsilateral iliac in a constrained state via a catheter or like device until the first attachment element 31 is disposed within the ipsilateral attachment element 14 of the main graft body section 12. The ipsilateral graft body section 27 is then released from the constrained state and the circumferential inflatable channels 33 of the first attachment element 31, the inflatable channels 38 and the ipsilateral sealing cuff 40 may then all be inflated by injection of inflation material into the ipsilateral fill port 40A. This causes the inflatable channels 33 of the first attachment element 31 to engage the circumferential inflatable channels 60 of the ipsilateral attachment element 14. The engagement of the ipsilateral attachment element 14 and first attachment element 31 is such that a seal is created between the elements 14 and 31. In addition, the engagement substantially prevents axial displacement of movement to separate the ipsilateral graft body section 27 in a distal direction relative to the ipsilateral attachment element 14 of the main graft body section 12. Both the main fill port 20 and ipsilateral fill port may include a valve, such as a one way valve 20A, that allows the injection of inflation material but prevents the escape thereof. The same or similar procedure is carried out with respect to the deployment of the contralateral graft body section in the contralateral attachment element 16 of the main graft body portion 12. Note that in the embodiment shown in
As discussed above, the inflation channels 21 of main graft body section 12, channels 38 of ipsilateral graft body section 27 and channels 52 of contralateral graft body section 41 may be inflated in any sequence and in any number of partial steps until the desired level of inflation is achieved, to effect the desired clinical result. As such, the deployment and inflation sequence described above is but one of a large number of sequences and methods by which the embodiments of the present invention may be effectively deployed.
The various embodiments of the present invention may also be used for deploying and joining multiple sections of non-bifurcated endoprostheses, which are useful, for example, in treating TAAs. Examples of such non-bifurcated devices, their delivery systems and methods for delivery are described in commonly-owned U.S. Pat. Nos. 6,331,191, 6,395,019, 6,733,521 to Chobotov et al. and pending U.S. patent application Ser. No. 10/327,711, the entirety of each of which are incorporated herein by reference. Two or more sections of tubular endoprostheses may be joined using the technologies described herein to achieve the desired length for effectively treating TAAs, aortic dissections, and other conditions in the thoracic or other sections of the aorta or other vessel in which a non-bifurcated endoprosthesis is indicated.
Referring to
Inflated circumferential inflatable channels 76 have reduced circumference shoulder portions 77 that engage reduced circumference shoulder portions 78 of the ipsilateral attachment element 71. Shoulder portions 78 are created by the outward pressure and displacement of the wall portion 75, which form recessed pockets in the wall portion 75 due to outward pressure from the circumferential inflatable channels 76. The strength and resilience of the reduced circumference shoulder portions 78 of the ipsilateral attachment element 71 is enhanced by the cylindrical stents 74 which provide greater resistance to outward displacement of the wall portion 75 than adjacent areas of the wall portion that do not include reinforcing stents 74. A flared reinforced segment 79 is disposed at the distal end of the first attachment element 72 and engages a tapered portion 80 of the ipsilateral attachment element 71 of the main graft body section 12. The flared reinforced segment 79 may include a resilient ring 81 disposed in the wall portion 75 of the flared reinforced segment 79 that is resistant to radial compression and expansion.
The engagement of the ipsilateral attachment element 71 and first attachment element 72 is such that a seal is created between the elements 71 and 72. In addition, the engage ment substantially prevents axial displacement of movement or separation of the ipsilateral graft body section 73 in a distal direction relative to the ipsilateral attachment element 71 of the main graft body section 12 and provides for a length adjustability in a fashion similar to the embodiment described in conjunction with
Referring to
When inflated circumferential inflatable channels 87 have reduced circumference shoulder portions 88 that engage reduced circumference shoulder portions 89 of the recessed circumferential pockets 86 of the ipsilateral attachment element 83. A flared reinforced segment 90 is disposed at the distal end of the first attachment element 84 and engages a tapered portion 91 of the ipsilateral attachment element 83 of the main graft body section 12. The flared reinforced segment 90 may include a resilient ring 92 disposed in the wall portion 86A of the flared reinforced segment 90 that is resistant to radial compression and expansion which provides further enhancement of the joint between the ipsilateral attachment element 83 and first attachment element 84.
The engagement of the ipsilateral attachment element 83 and first attachment element 84 is such that a seal is created between the elements 83 and 84. In addition, the engagement substantially prevents axial displacement of movement or separation of the ipsilateral graft body section 85 in a distal direction relative to the ipsilateral attachment element 83 of the main graft body section 12.
Referring to
Referring to
The first attachment element 97 has an enlarged segment 108 with a proximal reduced circumference shoulder portion 109 and a distal reduced circumference shoulder portion 110. The proximal reduced circumference shoulder portion 109 is reinforced by a proximal reinforcing stent 111 that is disposed in the first attachment element 97. The distal reduced circumference shoulder portion is reinforced by a distal reinforcing stent 112 that is also disposed in the first attachment element 97 distal of the stent 111. The reinforcing stents 111 and 112 provide a configuration that resists compressive forces that alter the nominal shape or configuration of the first attachment element 97. The first attachment element 97 also includes a circumferential inflatable channel 113 disposed in the wall portion 114 of the enlarged segment 108 that may be inflated with a pressurized inflation material, such as the inflation materials discussed above, in order to provide further resistance to compressive forces and provide an outward radial force against an inside surface 115 of the ipsilateral attachment element 96.
The first attachment element may be deployed in the reinforced recessed pocket 99 of the ipsilateral attachment element 96 by positioning the enlarged segment 108 of the first attachment element 97 within the reinforced recessed pocket 99 with the enlarged segment 108 in a radially constrained state. Thereafter, the radial constraint on the enlarged segment 108 is removed and the enlarged segment allowed to expand into the reinforced recessed pocket 99.
The first attachment element 121 includes a plurality of flexible loops 126 disposed adjacent each other, as shown in
It should be noted that the relative position of the plurality of flexible hooks 124 and flexible loops 126 could be reversed with the same advantage achieved. So long as the surfaces of the ipsilateral attachment element 119 and first attachment element 121 are mutually cohesive, specifically, mutually mechanically cohesive so as to prevent shear displacement, the same or similar result may be achieved. For some embodiments, the length of the flexible hooks may be from about 0.020 inch to about 0.050 inch. The length of the flexible loops may be from about 0.020 inch to about 0.050 inch.
The flared proximal end 127 of the first attachment element 121, which may also be reinforced with an appropriately sized stent (not shown), may provide a smooth fluid flow transition from the main fluid flow lumen 13 to the ipsilateral fluid flow lumen 123. In addition, the flared proximal end 127 may exert an outward radial force against the inside surface of the ipsilateral leg 120 and provide a seal between the main fluid flow lumen 13 and the ipsilateral fluid flow lumen 123.
Referring to
The ipsilateral attachment element 145 and first attachment element 157 may be mutually mechanically cohesive or otherwise configured to resist shear displacement when pressed together. Suitable combinations of surfaces, such as those discussed above with regard to
The mating of the ipsilateral attachment element 145 and first attachment element 157 is enhanced by the inward radial compression on the joint 160 produced by inflation of the inflatable cuff 158. The inflatable cuff 158 expands upon inflation as the cavity 159 fills with inflation material, however, expansion in an outward radial orientation is constrained by the stent 147 which is at least partially disposed over the cuff 158. As such, inflation of the inflatable cuff 158 applies radial compression on the joint 160 which enhances the strength of the joint 160. It should be noted that the same or similar effect could be achieved without the inflatable cuff 158 if the stent 147 was appropriately sized and configured to apply inward radial compression on the joint 160 when in a relaxed or compressed state. The joint 160 as shown in
The first attachment element 182 includes the expandable cylindrical member 172 which has a plurality of protuberances 170 disposed adjacent each other, as shown in
The expandable cylindrical member 172 may be made from a thin element 190 which is formed into the undulating cylindrical pattern as shown in the embodiment of
The expandable member 250 may also include barbs 252 which are configured to extend radially from the expandable member 250 and protrude through an inner wall 254 of the inflatable cuff 245 and into the inflation material 248. In some embodiments, the length and configuration of the barbs 252 are chosen so as to penetrate the inner wall 254 and into the inflation material 248 without penetrating an outer wall 256 of the inflatable cuff 245. The inflation material 248 shown in
In addition to an expandable member 250, the first attachment element 246 of the ipsilateral graft body section 242 may also include a connector ring 258 disposed in the PTFE material of the ipsilateral graft body section 242. The connector ring 258 may provide an anchor and strain relief function for the expandable member 250 which is secured thereto. The connector ring 258 may be secured inside, outside or within the wall of the ipsilateral graft body section 242. The portion of the ipsilateral graft body section 242 that surrounds the connector ring 258 may be flared or tapered to provide a smooth fluid flow transition from the main fluid flow lumen 13 to the ipsilateral fluid flow lumen 260 of the ipsilateral graft body section 242.
As shown in
While particular forms of embodiments of the invention have been illustrated and described, it will become apparent that various modifications may be made without departing from the spirit and scope of the invention. For example, while the illustrated endovascular grafts have a main graft body section and an ipsilateral graft body section and a contralateral graft body section, other embodiments of the present invention may only include one of the ipsilateral graft body section and the contralateral graft body sections. In such embodiments, the ipsilateral graft body section or the contralateral graft body section may be integrally formed with the main graft body section, and the other of the ipsilateral graft body section or contralateral graft body section may be attachable to the main graft body section. In addition, all of the embodiments of the present invention described herein may be used in non-bifurcated endoprosthesis applications to join or attach two or more such graft sections, especially for treating conditions in the thoracic aorta.
Moreover, while the illustrated embodiments have the ipsilateral graft body section and contralateral graft body section at least partially positioned within the ipsilateral leg and contralateral leg of the main graft body portion, it should be appreciated that in alternative embodiments it may be possible to have the ipsilateral leg and contralateral leg of the main graft body portion at least partially positioned within the ipsilateral graft body section and contralateral graft body section.
Accordingly, it is not intended that the invention be limited by the foregoing exemplary embodiments.
The present application claims benefit to U.S. Provisional Application Ser. No. 60/552,132 entitled “Modular Endovascular Graft,” filed Mar. 11, 2004, the complete disclosure of which is incorporated herein by reference.
Number | Date | Country | |
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60552132 | Mar 2004 | US |