US20030220667A1 - Method of containing embolic material in the left atrial appendage - Google Patents
Method of containing embolic material in the left atrial appendage Download PDFInfo
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- US20030220667A1 US20030220667A1 US10/364,910 US36491003A US2003220667A1 US 20030220667 A1 US20030220667 A1 US 20030220667A1 US 36491003 A US36491003 A US 36491003A US 2003220667 A1 US2003220667 A1 US 2003220667A1
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- Prior art keywords
- embolic material
- atrial appendage
- left atrial
- wire structure
- self expandable
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Abstract
Description
- This is a continuation application of U.S. patent application Ser. No. 09/435,562 filed on Nov. 8, 1999 which is a continuation-in-part of U.S. patent application Ser. No. 09/187,200, filed Nov. 6, 1998, now U.S. Pat. No. 6,152,144, the disclosures of which are incorporated in their entirety herein by reference.
- Embolic stroke is the nation's third leading killer for adults, and is a major cause of disability. There are over 700,000 strokes per year in the United States alone. Of these, roughly 100,000 are hemoragic, and 600,000 are ischemic (either due to vessel narrowing or to embolism). The most common cause of embolic stroke emanating from the heart is thrombus formation due to atrial fibrillation. Approximately 80,000 strokes per year are attributable to atrial fibrillation. Atrial fibrillation is an arrhythmia of the heart that results in a rapid and chaotic heartbeat that produces lower cardiac output and irregular and turbulent blood flow in the vascular system. There are over five million people worldwide with atrial fibrillation, with about four hundred thousand new cases reported each year. Atrial fibrillation is associated with a 500 percent greater risk of stroke due to the condition. A patient with atrial fibrillation typically has a significantly decreased quality of life due, in part, to the fear of a stroke, and the pharmaceutical regimen necessary to reduce that risk.
- For patients who develop atrial thrombus from atrial fibrillation, the clot normally occurs in the left atrial appendage (LAA) of the heart. The LAA is a cavity which looks like a small finger or windsock and which is connected to the lateral wall of the left atrium between the mitral valve and the root of the left pulmonary vein. The LAA normally contracts with the rest of the left atrium during a normal heart cycle, thus keeping blood from becoming stagnant therein, but often fails to contract with any vigor in patients experiencing atrial fibrillation due to the discoordinate electrical signals associated with AF. As a result, thrombus formation is predisposed to form in the stagnant blood within the LAA.
- Blackshear and Odell have reported that of the 1288 patients with non-rheumatic atrial fibrillation involved in their study, 221 (17%) had thrombus detected in the left atrium of the heart. Blackshear J L, Odell J A., Appendage Obliteration to Reduce Stroke in Cardiac Surgical Patients With Atrial Fibrillation. Ann Thorac. Surg., 1996.61(2):755-9. Of the patients with atrial thrombus, 201 (91%) had the atrial thrombus located within the left atrial appendage. The foregoing suggests that the elimination or containment of thrombus formed within the LAA of patients with atrial fibrillation would significantly reduce the incidence of stroke in those patients.
- Pharmacological therapies for stroke prevention such as oral or systemic administration of warfarin or the like have been inadequate due to serious side effects of the medications and lack of patient compliance in taking the medication. Invasive surgical or thorascopic techniques have been used to obliterate the LAA, however, many patients are not suitable candidates for such surgical procedures due to a compromised condition or having previously undergone cardiac surgery. In addition, the perceived risks of even a thorascopic surgical procedure often outweigh the potential benefits. See Blackshear and Odell, above. See also Lindsay B D., Obliteration of the Left Atrial Appendage: A Concept Worth Testing, Ann Thorac. Surg., 1996.61(2):515.
- Despite the various efforts in the prior art, there remains a need for a minimally invasive method and associated devices for reducing the risk of thrombus formation in the left atrial appendage.
- There is provided in accordance with one aspect of the present invention, a method of containing embolic material within a left atrial appendage of a patient. The method comprises the steps of providing a containment device comprising a barrier for preventing the escape of embolic material from the left atrial appendage. A delivery catheter is provided, having a proximal end and a distal end. The delivery catheter is advanced through the patient's vasculature to position the containment device within the patient's left atrium. The containment device is deployed such that the barrier substantially obstructs the passage of embolic material from the left atrial appendage. In one implementation of the invention, the barrier comprises a mesh. The barrier may comprise polyethylene. Alternatively, the barrier may comprise a nickel titanium alloy, or other materials disclosed herein. The barrier may comprise a self expandable frame, and may further carry a mesh on the frame. The self expandable frame may comprise a wire mesh.
- In accordance with another aspect of the present invention, there is provided a method of treating the left atrial appendage of a patient. The method comprises the steps of providing a delivery catheter having a proximal end and a distal end, and a self expandable wire structure for acting as a barrier to the passage of embolic material from the left atrial appendage, removably carried by the distal end. The delivery catheter is advanced into the patient's left atrium. The self expandable wire structure is positioned at the left atrial appendage, and the self expandable wire structure is deployed such that it substantially obstructs the passage of embolic material from the left atrial appendage.
- The method may additionally comprise the step of removing thrombotic or fibrotic material from the patient's left atrial appendage prior to deployment of the self expandable wire structure. The deploying step may comprise deploying the self expandable wire structure such that it engages at least a portion of an inner surface of the left atrial appendage. The self expandable wire structure may comprise wire mesh. The self expandable wire structure may comprise a plurality of tissue engagement members, and the method further comprises the step of engaging tissue with the tissue engagement members.
- Further features and advantages of the present invention will become apparent to those of ordinary skill in the art in view of the detailed description of preferred embodiments which follows, when considered together with the attached drawings and claims.
- FIG. 1 shows a perspective view of an embodiment having features of the invention with an occluding member and a retention member.
- FIG. 2 shows an end view of the apparatus of FIG. 1 in partial section.
- FIG. 3 shows a longitudinal cross-sectional view of the apparatus of FIGS. 1 and 2.
- FIG. 3A shows a perspective view of an apparatus having features of the invention.
- FIG. 3B shows an elevational view in partial section of the apparatus of FIG. 3A.
- FIG. 4 shows an elevational view of an apparatus having features of the invention in a deployed state within a body cavity.
- FIG. 5 shows an elevational view of an apparatus having features of the invention in a deployed state within a body cavity.
- FIG. 6 shows a perspective view of an apparatus for sealing off a body cavity having features of the invention.
- FIG. 7 shows an elevational view in partial section of an apparatus for sealing off a body cavity having features of the invention.
- FIG. 8 shows a transverse cross-sectional view of the apparatus of FIG. 7 taken along lines8-8.
- FIG. 9 shows a schematic view of a patient's heart with a transeptal catheter deployed through the septum and a delivery catheter and apparatus for sealing off a body cavity disposed therein.
- FIG. 10 shows a schematic view of a patient's heart in partial section with a delivery catheter disposed within the opening of the LAA.
- FIG. 11 shows a magnified view of the delivery catheter distal end and the LAA of a patient of FIG. 10 with an apparatus for sealing off a body cavity partially deployed within the LAA.
- FIG. 12 shows the apparatus for sealing off a body cavity of FIG. 11 fully deployed within a LAA.
- FIG. 13 shows an elevational view of a device for occluding a body cavity having features of the invention.
- FIG. 14 shows a transverse cross sectional view of the device for occluding a body cavity of FIG. 13 taken along lines14-14.
- FIG. 15 shows a device for occluding a body cavity having features of the invention deployed within a LAA.
- FIG. 16 shows a device for occluding a body cavity having features of the invention deployed within a LAA.
- FIG. 17 shows a LAA being occluded by a method having features of the invention.
- FIG. 18 shows a LAA occluded by method having features of the invention.
- FIG. 19 shows a LAA occluded by method having features of the invention.
- FIG. 20 is an elevational view of an apparatus for closing an interior body cavity of a patient in partial section having features of the invention.
- FIG. 21 is a schematic view of an apparatus for closing an interior body cavity of a patient in contact with tissue of a LAA.
- FIG. 22 is a schematic view of an apparatus for closing an interior body cavity of a patient in contact with tissue of a LAA.
- FIG. 23 shows a LAA which has been closed by a method having features of the invention.
- FIG. 24 is a perspective view of an occlusion device in accordance with the present invention.
- FIG. 25 is a side elevational view of the occlusion device shown in FIG. 24.
- FIG. 26 is a perspective view of an alternate embodiment of the present invention.
- FIG. 27 is a side elevational view of the embodiment shown in FIG. 26.
- FIG. 28 is a perspective view of a further embodiment of the present invention.
- FIG. 29 is a side elevational view of the embodiment of FIG. 28.
- FIG. 30 is a perspective view of a further occlusion device in accordance with the present invention.
- FIG. 31 is an end view taken along the line31-31 of FIG. 30.
- FIG. 32 is a schematic illustration of an inflatable balloon positioned within the occlusion device of FIG. 30.
- FIG. 33 is a schematic view of a pull string deployment embodiment of the occlusion device of FIG. 30.
- FIGS. 34A and 34B are side elevational schematic representations of partial and complete barrier layers on the occlusion device of FIG. 30.
- FIG. 35 is a side elevational schematic view of an alternate occlusion device in accordance with the present invention.
- FIG. 36 is a schematic view of a bonding layer mesh for use in forming a composite barrier membrane in accordance with the present invention.
- FIG. 37 is an exploded cross sectional view of the components of a composite barrier member in accordance with the present invention.
- FIG. 38 is a cross sectional view through a composite barrier formed from the components illustrated in FIG. 37.
- FIG. 39 is a top plan view of the composite barrier illustrated in FIG. 38.
- FIGS.1-3 show an embodiment of an occluding
device 10 having features of the invention where an occludingmember 11 is secured to aretention member 12 that is arranged to fix the occluding member in a desired position within a body passageway or cavity. The occludingmember 11 generally has disc shape with anouter rim 13 around the perimeter of aframe structure 14 which supports abarrier 15. Theouter rim 13 can be circular or polygonal, or any other shape that is suitable for conforming to the inside surface of a body cavity. Ahub 16 can be located near the center of the occludingmember 11 which serves to connect theretention member 12 to the occluding member, in addition to other functions. Theouter rim 13 is typically made from asoft polymer material 17 which permits flexibility of the outer rim and facilitates sealing of the outer rim against the inside surface of a body cavity or passageway. Thebarrier 15 can be a thin mesh or film of material which serves to block the passage of material within an area surrounded by theouter rim 13. Thebarrier 15 can be secured to theouter rim 13 along itsentire perimeter 18 in order to achieve a complete seal therebetween and can be molded into theouter rim 13 or bonded thereto by a suitable method such as gluing, welding, sewing or other suitable method. - The
outer rim 13 is at least partially supported by theframe structure 14 which connects the outer rim and the hub. Theframe structure 14 can be made from one or more elements of high strength material such as stainless steel or MP35N, or may preferably be made from shape memory or pseudoelastic alloys such as NiTi, or any of a variety of known structural biodegradable materials (e.g. polyglycolic acid, poly lactic acid, poly-L-lactic acid and derivatives or copolymers such as PLGA). Preferably, theframe structure 14 is made from a material which can be self-expanding from a constrained configuration so that the occludingdevice 10 can be delivered to the deployment site in a low profile an flexible configuration which facilitates percutaneous delivery. - Preferably a
radial hoop 21 is contained within thesoft polymer material 17 of theouter rim 13 and serves to maintain the annular shape of the outer rim and facilitate radial expansion of the outer rim from a constrained position or configuration. Theradial hoop 21 may be isolated within thesoft polymer material 17 of theouter rim 13, or may be connected to at least some of theelements 22 of theframe structure 14, in order to have stronger mechanical joint between the outer rim and the frame structure. Theradial hoop 21 is shown in a substantially circular configuration, but may also be polygonal or otherwise suitably shared, and may have connections or joints spaced thereon to facilitate contraction or folding of the device for non-invasive delivery. - In addition to connecting the
retention member 12 and the occludingmember 11, thehub 16 may serve to house arotational coupling 23 which is connected to theproximal end 24 of atissue penetrating shaft 25 within the retention member. Therotational coupling 23 allows the transfer of torque to thetissue penetrating shaft 25 which preferably has a helically shaped extension ordistal extremity 26 which is configured to screw into tissue and be mechanically fixed thereto. Longitudinal movement of thetissue penetrating shaft 25 relative to theretention member 12 andhub 16 may be prevented by sizing alumen 27 of the retention member which contains the tissue penetrating shaft such that the helically shapedextension 26 at the distal end is too large to pass through the lumen and theproximal end 24 of the tissue penetrating shaft is prevented from passing through the lumen by the rotational coupling attached thereto. Therotational coupling 23 may also be configured to be longitudinally captured by thehub 16 but still be rotatably disposed therein. - FIGS. 3A and 3B depict an alternative embodiment of an occluding
device 10 having an occludingmember 11 and aretention member 12. Theretention member 12 has ashaft 28 and radially extendingmembers 29 extending radially from a proximal end of the shaft. Theradially extending members 29 serve to anchor theshaft 28 and the occludingmember 11 by engaging the tissue surrounding the occluding device. Preferably, the radially extending members are self-expanding from a constricted state and are made of a pseudo elastic alloy such as NiTi, or a high strength material such as stainless steel. Although it is preferable for theradially extending members 29 to be self-expanding from a constricted state, they may also be expanded by use of shape memory properties or a radial outward force as would be provided by an inflatable balloon or the like. Theshaft 28 can be a single element or made of multiple elements, and can be made from the same materials as the radially extending members or different materials such as polymers or polymer composites. Theradially extending members 29 have a proximally directed bias at theirradial extremities 29A so that the members readily fold down and move easily in a distal direction during insertion of the occludingdevice 10, but spring outward and aggressively engage surrounding tissue upon movement in a proximal direction. This configuration of theradially extending members 29 allows easy insertion into a body cavity, but prevents egress of thedevice 10 in and outward or proximal direction. - FIG. 4. depicts an occluding
device 30 similar to that depicted in FIGS. 1-3 deployed within the leftatrial appendage 31 of a patient. An outer rim orperiphery 32 of the occludingdevice 30 is disposed adjacent theopening 33 of the leftatrial appendage 31 in a position which allows for a substantial seal of the outer rim against theinside surface 34 of the LAA. A helically shapeddistal extremity 35 of atissue penetrating shaft 36 has been screwed into the wall tissue of the LAA and is mechanically secured thereto. Aretention member 38 maintains the position of an occludingmember 41 in a substantially perpendicular orientation with respect to a longitudinal axis of theLAA 42. - FIG. 5 depicts an occluding device similar to that depicted in FIGS.1-4 deployed within a
LAA 51 of a patient similar to what is shown in FIG. 4. The structure of an occludingmember 52 of the embodiment as shown in FIG. 5 differs from that shown in FIG. 4 in that abarrier 53 andframe structure 54 of the embodiment of FIG. 5 protrudes proximally from a plane defined by anouter rim 55. This configuration may be useful for certain morphologies of patient's LAAs. One object of the invention is to create a smooth surface outside the body passageway or cavity in order to prevent turbulent flow or eddies of blood or other bodily fluid within the cavity or passageway. The alternative configuration of the occludingdevice 50 shown in FIG. 5 may be useful in this regard. - FIG. 6 shows an alternative embodiment of an occluding
device 60 which has an occludingmember 61, aframe structure 62, abarrier 63 and a retention member in the form of anexpandable member 65 which has linkedelements 66 that are preferably expandable from a constrained configuration. Theexpandable member 65 is generally cylindrical in shape and can have a series of circumferential linkedelements 66 connected bylinks 68. Although FIG. 6 depicts theexpandable member 65 as a series of linkedelements 66, those skilled in the art will realize that a similar effect can be achieved with a single wire in a helical configuration or a plurality of wires in a mesh or braided configuration, or any other suitable configuration that can be self-expanding from a constrained configuration or expanding with the application of heat or other form of energy or force. For example, theexpandable member 65 may be configured to be deployed by an outward radial force delivered from within the expandable member. An inflatable balloon or the like could be used to exert such a force. The expandable member is preferably secured to anouter rim 71 of the occludingmember 61 but may also be secured to theframe structure 62 directly or indirectly. Theexpandable member 65 can be self-expanding from a constrained configuration as can the occludingmember 61 and theframe structure 62 andouter rim 71 thereof. Theframe structure 62,outer rim 71 andbarrier 63 may have construction similar to that described above with regard to the similar elements of the embodiments depicted in FIGS. 1-5. - Referring to FIG. 7, the
expandable member 65 as shown in FIG. 6 may also have asheath 72 disposed around it so as to act as a shield between the expandable member and an inner surface of a patient's body cavity or passageway. Thesheath 72 may facilitate the sealing function of the occludingmember 61, but is primarily intended to prevent damage to either tissue on the inside surface of a body cavity or to the linkedelements 66 of the expandable member. Thesheath 72 may surround all or part of theexpandable member 65 and may be made from a variety of suitable biocompatible materials such as Dacron®, Nylon, TFE, PTFE or ePTFE. Thesheath 72 may be a weave, braid, film or have any other suitable configuration.Expandable member 65 may also be coated by dipping, spraying, or other suitable process with a friction reducing material such as Teflon®, or with an active compound such as heparin. - FIG. 8 shows a transverse cross-sectional view of the embodiment of FIG. 7 taken at lines8-8. The
frame structure 62 has an axis orhub 73 disposed at approximately the center of the frame structure which serves to connect the variousradial elements 74 of the frame structure. Thehub 73 can have an independent structure that links theseveral elements 74 of theframe structure 62 or it may be merely the terminus of the various frame structure elements and have a solid composition. In either structure, thehub 73 preferably allows a constrained configuration of the occludingmember 61 to facilitate percutaneous delivery of the occludingdevice 60. Thehub 73 may also have a lumen disposed therein to allow passage of a guidewire of other guiding member. Preferably, the lumen would have a self sealing valve or gasket which prevents the passage of fluid or embolic material once the guidewire or guiding member is removed from the lumen. - Referring to FIG. 9, a schematic view of a patient's
heart 80 in partial section shows a trans-septal catheter 81 having aproximal end 82 and adistal end 83. Thedistal end 83 of the trans-septal catheter 81 is disposed within a patient'sheart 80 with thedistal end 84 of adelivery catheter 85 extending from thedistal end 83 of the trans-septal catheter. Thedistal end 83 of the trans-septal catheter 81 has breached theseptum 86 of the patient'sheart 80 and is disposed adjacent the opening of the patient'sLAA 88. At theproximal end 82 of the trans-septal catheter 81 there is aLuer connector 91 coupled to ahemostasis valve 92 which prevents the egress of blood from alumen 93 of the trans-septal catheter 81. The proximal end 94 of thedelivery catheter 85 extends proximally from thehemostasis valve 92 and has aLuer connector 95 attached to the proximal extremity thereof. Theproximal end 96 of, aplunger 97 extends from theLuer connector 95 of the delivery catheter. The proximal end 94 of the delivery catheter is arranged to allow rotational and axial movement of theplunger 97 while preventing blood or other bodily fluids from leaking between thedelivery catheter 85 and theplunger 97. - Referring to FIG. 10, a patient's
heart 80 is shown in partial section with thedistal end 84 of adelivery catheter 85 disposed within theLAA opening 87. FIG. 11 is a magnified view of theLAA 88 shown in FIG. 10 and the distal end of thedelivery catheter 84, which is shown in partial section, contains aplunger 97 which is slideably disposed within aninner lumen 98 of thedelivery catheter 85 and serves to apply axial force in a distal direction on the collapsed occludingmember 101 disposed within the delivery catheter so as to force the occludingdevice 102 from the delivery catheter and deploy it. Anoccluding device 102 having anexpandable member 103 and an occludingmember 101 secured thereto is partially deployed and extending from the distal end of thedelivery catheter 84 into the patient'sLAA 88. The occludingdevice 102 can also be guided into the patient'sLAA 88 by use of an appropriate guidewire or guiding member. - FIG. 12 shows the
occluding device 102 of FIG. 11 in a deployed state within the patient'sLAA 88. Anouter rim 104 of the occludingmember 101 is in substantial sealing contact with theinside surface 105 of theLAA 88. Theexpandable member 103 has expanded so as to contact theinside surface 105 of the LAA and secure theoccluding device 102 thereto and maintain the occludingmember 101 in a substantially perpendicular orientation relative to a longitudinal axis 106 of theLAA 88. Abarrier 107 is disposed within an area bounded by theouter rim 104 and is positioned to prevent the passage or embolic or other material to or from theLAA 88. Thedistal end 108 of theplunger 97 is extending from the distal end of thedelivery catheter 84 after having pushed theoccluding device 102 from the delivery catheter. - Referring to FIG. 13, an
occluding device 110 having features of the invention is shown. The occludingdevice 110 has adelivery catheter 111 with adistal end 112, adetachment mechanism 113 disposed on the distal end of the delivery catheter and an occlusive body orinflatable member 114 detachably secured to the detachment mechanism. Theinflatable member 114 has a proximal end 115 and adistal end 116 with the proximal end being attached to thedetachment mechanism 113 and the distal end terminating at anend cap 117. Theinflatable member 114 has anoutside surface 118 that may contain a fibrosis inducing material such as Dacron® or other similar materials. Theinflatable member 114 may be made from a fluid tight film of polymer material which can be either compliant or non-compliant. Preferably theinflatable member 114 is made from silicone, however, any suitable material such as polyethylene, polyurethane or PET can be used. - The
detachment mechanism 113 can be activated by mechanical force or by delivery of thermal or optical energy by a suitable conduit. Alternatively, the inflatable member can be pushed into the LAA from thedelivery catheter 111 by an elongate push member without the use of a detachment mechanism. Theinflatable member 114 can be filled with a gas, fluid or gel which is injected under pressure through thedelivery catheter 114 and into the inflatable member. Suitable fluids to inject would include saline and silicone. Theinflatable member 114 may also be filled with a polymer material that can be hardened. Autologus fluid such as blood, or collagen may also be used. A fluid, gel or polymer used to fill the inflatable member may contain contrast agents such as gold, tantalum, bismuth, barium sulfate or the like in order to improve visualization under fluoroscopy or x-ray imaging. - FIG. 14 is a transverse cross-sectional view of the
occluding device 110 of FIG. 13 taken along lines 14-14. An optionalinner shaft 121 is shown disposed within theinflatable member 114, preferably in a concentric arrangement. Theinner shaft 121 provides longitudinal axial support to theinflatable member 114 so as to maintain a longitudinal dimension of theinflatable member 114 when it is being inflated and deployed. Theinner shaft 121 may be solid or contain one or more lumens that may or may not be in fluid communication with aninner lumen 122 of theinflatable member 114, and can be used for the passage of a guidewire or guiding member. - FIG. 15 depicts an alternative embodiment of an
occluding device 110 which consists of aninflatable member 114 similar to the inflatable member of FIG. 13, shown substantially deployed, within a patient'sLAA 123. Theinflatable member 114 has been at least partially filled with a fluid, gas or gel within the patient'sLAA 123 such that the outside surface of theinflatable member 118 is in contact with at least part of theinside surface 124 of the LAA. Theinflatable member 114 can haverib members 125 which can mechanically interlock with thetrebeculae 126 of the inside surface of theLAA 124 or other surface irregularities of the inside surface of a patient's body cavity or passageway. Therib members 125 form a complete circumference of theinflatable member 114, but could also form a partial circumference, spiral configuration, or consist of random projections on the surface of theinflatable member 118. Therib members 125 should extend radially about 1 to about 4 mm from the nominal surface of theinflatable member 114, and are preferably spaced about 3 to about 8 mm from each other. Therib members 125 may be made from any suitable polymer material, but are preferably made from the same material as the inflatable member, and are integrally molded thereon, or bonded thereto with a heat weld or adhesive bond suitable for bonding flexibly medical polymers. Theinflatable member 114 is depicted with the distal end of thedelivery catheter 112 anddetachment mechanism 113 attached. As an alternative, or in addition to thepolymer rib members 125 shown in FIG. 15, barbs or hooks could be secured to the outside surface of theinflatable member 114 which are configured to engage the inside surface of a patient'sLAA 124. Preferably, barbs or hooks disposed on the outside surface of the inflatable member and configured to engage the tissue of the inside surface of a patient'sLAA 124 would have a proximally directed bias at their radial extremity so that the barbs would fold down and move easily in a distal direction during insertion of theinflatable member 114, but would spring outward and aggressively engage the tissue of the body cavity upon movement in a proximal direction of the inflatable member. - FIG. 16 depicts an
occluding device 110 consisting of aninflatable member 114 which is shown deployed within a patient'sLAA 123. The embodiment of theinflatable member 114 shown in FIG. 16 has anoptional retention member 127 with atissue penetrating shaft 128 which has a proximal 131 end and adistal end 132. A rotational coupling 133 is disposed at the proximal end 131 of thetissue penetrating shaft 128 and a helically shapedextremity 134 is disposed at the distal end of theshaft 132. The helically shapeddistal extremity 134 is shown deployed within and mechanically engagingwall tissue 135 of the LAA so as to secure theinflatable member 114 and maintain its position within theLAA 123 of the patient. - FIG. 17 shows an alternative embodiment of an
occlusive member 140 consisting of apolymer mass 141 which has been injected or delivered into a patient'sLAA 142. Thedistal end 143 of adelivery catheter 144 has alumen 145 therein which extends to a proximal end of the delivery catheter which is in fluid communication with a source of pressurized polymer material. A source ofpressurized polymer material 146 can be any type of pump or device capable of forcing a polymer fluid or gel into the proximal end of the delivery catheter with sufficient pressure to force the polymer fluid or gel out thedistal end 143 of thedelivery catheter 144 and into a patient's body cavity or passageway. Thedelivery catheter 144 may be positioned by the techniques discussed above, e.g., the Mullins trans-septal approach or any other suitable method. Once the distal end of thedelivery catheter 143 is disposed within a desired portion of the patient'sLAA 142, thepolymer mass 141 may be injected to fill the cavity to the desired level. TheLAA 142 can be completely or partially filled with thepolymer mass 141 which can be formulated to harden over time, with heat or remain in a fluid or gel state. The distal end of the delivery catheter can optionally include an expandable member which is used to substantially seal the delivery catheter against the inside surface of the opening of the patient's body cavity during the delivery of polymer material. The expandable member can be an inflatable balloon or the like which are well known in the art. - Optionally, a
retention member 127 having atissue penetrating shaft 128 or the like, such as shown in FIG. 16 with regard to theinflatable member 114, may be deployed within theLAA 142 prior to injection of thepolymer mass 141 and captured thereby so as to secure the polymer mass within the LAA. Alternatively, the polymer mass can be used to fill the patient's LAA and surround and secure a deployed device as shown in FIG. 4 or 5 in the patient'sLAA 142. - Once a desired amount of
polymer mass 141 has been injected into theLAA 142, as assessed for example by TE Echo imaging, thedelivery catheter 144 may be withdrawn and the procedure terminated. Preferably, theentire LAA 142 of a patient is filled with thepolymer mass 141 as shown in FIG. 18 and hardens or gels to maintain its shape. It may be desirable to have thepolymer mass 141 retain a soft compressible form after setting or hardening so that it is at least partially compliant with the constrictive pumping action of a heart and resistant to fatigue as a result thereof. A material used to form thepolymer mass 141 may contain contrast agents such as gold, platinum, tantalum, bismuth or the like in order to better visualize the deployment of the polymer mass under fluoroscopic or x-ray imaging. - Another alternative embodiment of an
occlusive member 140 can be found in FIG. 19 which shows anocclusive coil 147 which has been deployed within anLAA 142. Theocclusive coil 147 as shown has assumed a random configuration that is mechanically occluding theLAA 142 and which has induced clot and/orfibrosis formation 148 which further facilitates occlusion of theLAA 142. - An apparatus for closing off a body cavity or
passageway 150 is shown in FIG. 20 which has features of the present invention. Theapparatus 150 has anelongate shaft 151 with aninner lumen 152 and aproximal end 153 and adistal end 154. Slideably disposed within theinner lumen 152 of theelongate shaft 151 are at least twoelongate members 155 which haveproximal ends 156 anddistal ends 157 and havetissue attachment members 158 disposed on the distal ends. An optionaldistal anchor member 161 is also slideably disposed within theinner lumen 152 of theelongate shaft 151 and preferably has adistal end 162 terminating with ahelical member 163. Theproximal end 153 of theelongate shaft 151 has aproximal control module 164 which seals theinner lumen 152 of theelongate shaft 151 and allows rotation and translation of the proximal ends 156 of theelongate members 155 and thedistal anchor member 161 while maintaining a seal between said members to prevent leakage of bodily fluids therefrom. Theproximal control module 164 can optionally be configured to control advancement and retraction of theelongate members 155 and control activation of thetissue attachment members 158. - FIG. 21 shows the apparatus for closing off a
body cavity 150 of FIG. 20 with the distal ends of theelongate members 157 and thetissue attachment members 158 extending distally from the distal end of theelongate shaft 154. The distal ends of theelongate members 157 are angled or deflected from alongitudinal axis 165 of theelongate shaft 151 so as to engagetissue 166 of theopening 167 of theLAA 168 as shown. Theelongate members 155 may be deflected by an abutment or angulation contained in the distal end of theelongate shaft 154, but are preferably preshaped in an angled configuration which manifests when the distal ends are freed of the constraint of theinner lumen 152 of the elongate shaft an allowed to assume their relaxed preshaped condition. Thehelical member 163 at thedistal end 162 of thedistal anchor member 161 is engaged with thewall tissue 171 of theLAA 168 so as to provide an optional anchor that can be used to move theelongate shaft 151 relative to thedistal anchor member 161 and give greater control of the longitudinal axial movement of the elongate shaft relative to theLAA opening 167. Thetissue attachment members 158 are shown attached to theannular edge 172 of theLAA opening 167. Once thetissue attachment members 158 are attached, a closure member or retainingring 173 may be advanced distally by applying axial force on anelongate push shaft 174 which draws thetissue attachment members 158 and the tissue attached thereto closer together as shown in FIG. 22. As theclosure member 173 is further advanced distally, the annular edge of theLAA 172 is drawn closed, and eventually, the annular edge of the LAA will be completely closed into a closed state with theclosure member 173 surrounding and compressing the tissue of the annular edge as shown in FIG. 23. Once a closed state of the LAA is achieved, thetissue attachment members 158 may be detached, and the apparatus for closing off abody cavity 150 withdrawn. One alternative method can have thetissue attachment members 158 drawn together by retracting them proximally into thedistal end 154 of theelongate shaft 151 as opposed to distally advancing theclosure member 173 with theelongate push shaft 174. In this way, the annular edge of theLAA 172 can be drawn into a closed state within thedistal end 154 of theelongate shaft 151 at which point the annular edge may be fixed in the closed state by a variety of methods including suturing, tissue welding, the application of a suitable biocompatible adhesive, surgical staples or the like. - Referring to FIGS. 24 and 25, there is illustrated an alternate embodiment of the
occlusion device 10 in accordance with the present invention. Theocclusion device 10 comprises an occludingmember 11 comprising aframe 14 and abarrier 15. In the illustrated embodiment, theframe 14 comprises a plurality of radially outwardly extendingspokes 17 each having a length within the range of from about 0.5 cm to about 2 cm from ahub 16. In one embodiment, the spokes have an axial length of about 1.5 cm. Depending upon the desired introduction crossing profile of thecollapsed occlusion device 10, as well as structural strength requirements in the deployed device, anywhere within the range of from about 3 spokes to about 40 spokes may be utilized. In some embodiments, anywhere from about 12 to about 24 spokes are utilized, and, 18 spokes are utilized in one embodiment. - The spokes are advanceable from a generally axially extending orientation such as to fit within a tubular introduction catheter to a radially inclined orientation as illustrated in FIG. 24 and FIG. 25 following deployment from the catheter. In a self-expandable embodiment, the spokes are biased radially outwardly such that the occlusion member expands to its enlarged, implantation cross-section under its own bias following deployment from the catheter. Alternatively, the occlusion member may be enlarged using any of a variety of enlargement structures such as an inflatable balloon.
- Preferably, the spokes comprise a metal such as stainless steel, Nitinol, Elgiloy, or others which can be determined through routine experimentation by those of skill in the art. Wires having a circular or rectangular cross-section may be utilized depending upon the manufacturing technique. In one embodiment, rectangular cross section spokes are cut such as by known laser cutting techniques from tube stock, a portion of which forms the
hub 16. - The
barrier 15 may comprise any of a variety of materials which facilitate cellular in-growth, such as ePTFE. The suitability of alternate materials forbarrier 15 can be determined through routine experimentation by those of skill in the art. Thebarrier 15 may be provided on either one or both sides of the occlusion member. In one embodiment, thebarrier 15 comprises two layers, with one layer on each side of theframe 14. The two layers may be bonded to each other around thespokes 17 in any of a variety of ways, such as by heat bonding with or without an intermediate bonding layer such as polyethylene or FEP, adhesives, sutures, and other techniques which will be apparent to those of skill in the art in view of the disclosure herein. Thebarrier 15 preferably has a thickness of no more than about 0.003″ and a porosity within the range of from about 5 Pm to about 60 Pm. - The
barrier 15 in one embodiment preferably is securely attached to theframe 14 and retains a sufficient porosity to facilitate cellular ingrowth and/or attachment. One method of manufacturing a suitablecomposite membrane barrier 15 is illustrated in FIGS. 36-39. As illustrated schematically in FIG. 36, abonding layer 254 preferably comprises a mesh or other porous structure having an open surface area within the range of from about 10% to about 90%. Preferably, the open surface area of the mesh is within the range of from about 30% to about 60%. The opening or pore size of thebonding layer 254 is preferably within the range of from about 0.005 inches to about 0.050 inches, and, in one embodiment, is about 0.020 inches. The thickness of thebonding layer 254 can be varied widely, and is generally within the range of from about 0.0005 inches to about 0.005 inches. In a preferred embodiment, thebonding layer 254 has a thickness of about 0.001 to about 0.002 inches. One suitable polyethylene bonding mesh is available from Smith and Nephew, under the code SN9. - Referring to FIG. 37, the
bonding layer 254 is preferably placed adjacent one or both sides of a spoke orother frame element 14. Thebonding layer 254 and frame 14 layers are then positioned in-between afirst membrane 250 and asecond membrane 252 to provide a composite membrane stack. Thefirst membrane 250 and second 252 may comprise any of a variety of materials and thicknesses, depending upon the desired functional result. Generally, the membrane has a thickness within the range of from about 0.0005 inches to about 0.010 inches. In one embodiment, themembranes - The composite stack is heated to a temperature of from about 200° to about 300°, for about 1 minute to about 5 minutes under pressure to provide a finished composite membrane assembly with an embedded
frame 14 as illustrated schematically in FIG. 38. The final composite membrane has a thickness within the range of from about 0.001 inches to about 0.010 inches, and, preferably, is about 0.002 to about 0.003 inches in thickness. However, the thicknesses and process parameters of the foregoing may be varied considerably, depending upon the materials of thebonding layer 254 thefirst layer 250 and thesecond layer 252. - As illustrated in top plan view in FIG. 39, the resulting finished composite membrane has a plurality of “unbonded” windows or
areas 256 suitable for cellular attachment and/or ingrowth. Theattachment areas 256 are bounded by theframe 14 struts, and the cross-hatch pattern formed by thebonding layer 254. In the illustrated embodiment, the filaments of thebonding layer 254 are oriented in a nonparallel relationship with the struts offrame 14, and, in particular, at an angle within the range of from about 15° to about 85° from the longitudinal axis of the struts. Preferably, aregular window 256 pattern is produced. - The foregoing procedure allows the bonding mesh to flow into the first and
second membranes composite membrane 15 greater strength (both tensile and tear strength) than the components without the bonding mesh. The composite allows uniform bonding while maintaining porosity of themembrane 15, to facilitate tissue attachment. By flowing the thermoplastic bonding layer into the pores of the outer mesh layers 250 and 252, the composite flexibility is preserved and the overall composite layer thickness can be minimized. - The
occlusion device 10 may be further provided with a bulking element orstabilizer 194. Thestabilizer 194 may be spaced apart along an axis from the occludingmember 11. In the illustrated embodiment, adistal end 190 and aproximal end 192 are identified for reference. The designation proximal or distal is not intended to indicate any particular anatomical orientation or deployment orientation within the deployment catheter. As shown in FIGS. 24 and 25, thestabilizer 194 is spaced distally apart from the occludingmember 11. - For use in the LAA, the occluding
member 11 has an expanded diameter within the range of from about 1 cm to about 5 cm, and, in one embodiment, about 3 cm. The axial length of the occludingmember 11 in an expanded, unstressed orientation from thedistal end 192 to theproximal hub 16 is on the order of about 1 cm. The overall length of theocclusion device 10 from thedistal end 192 to theproximal end 190 is within the range of from about 1.5 cm to about 4 cm and, in one embodiment, about 2.5 cm. The axial length of thestabilizer 194 betweendistal hub 191 andproximal hub 16 is within the range of from about 0.5 cm to about 2 cm, and, in one embodiment, about 1 cm. The expanded diameter of thestabilizer 194 is within the range of from about 0.5 cm to about 2.5 cm, and, in one embodiment, about 1.4 cm. The outside diameter of thedisial hub 191 andproximal hub 16 is about 2.5 mm. - Preferably, the
occlusion device 10 is provided with one or more retention structures for retaining the device in the left atrial appendage or other body lumen. In the illustrated embodiment, a plurality of barbs orother anchors 195 are provided, for engaging adjacent tissue to retain theocclusion device 10 in its implanted position and to limit relative movement between the tissue and the occlusion device. The illustrated anchors are provided on one or more of thespokes 17, or other portion offrame 14. Preferably, every spoke, every second spoke or every third spoke are provided with one or two anchors each. The illustrated anchor is in the form of a barb, for extending into tissue at or near the opening of the LAA. - One or
more anchors 195 may also be provided on thestabilizer 194, such that it assists not only in orienting theocclusion device 10 and resisting compression of the LAA, but also in retaining theocclusion device 10 within the LAA. Any of a wide variety of structures may be utilized foranchor 195, either on the occludingmember 11 or thestabilizer 194 or both, such as hooks, barbs, pins, sutures, adhesives and others which will be apparent to those of skill in the art in view of the disclosure herein. - In use, the
occlusion device 10 is preferably positioned within a tubular anatomical structure to be occluded such as the left atrial appendage such that the occludingmember 11 is positioned across or near the opening to the LAA and thestabilizer 194 is positioned within the LAA. Thestabilizer 194 assists in the proper location and orientation of the occludingmember 11, as well as resists compression of the LAA behind the occludingmember 11. The present inventors have determined that following deployment of an occludingmember 11 without astabilizer 194 or other bulking structure to resist compression of the LAA, normal operation of the heart may cause compression and resulting volume changes in the LAA, thereby forcing fluid past the occludingmember 11 and inhibiting or preventing a complete seal. Provision of astabilizer 194 dimensioned to prevent the collapse or pumping of the LAA thus minimize leakage, and provision of the barbs facilitates endothelialization or other cell growth across the occludingmember 11. - For this purpose, the
stabilizer 194 is preferably movable between a reduced cross-sectional profile for transluminal advancement into the left atrial appendage, and an enlarged cross-sectional orientation as illustrated to fill or to substantially fill a cross-section through the LAA. The stabilizing member may enlarge to a greater cross section than the anatomical cavity, to ensure a tight fit and minimize the likelihood of compression. One convenient construction includes a plurality ofelements 196 which are radially outwardly expandable in response to axial compression of adistal hub 191 towards aproximal hub 16.Elements 196 each comprise adistal segment 198 and aproximal segment 202 connected by abend 200. Theelements 196 may be provided with a bias in the direction of the radially enlarged orientation as illustrated in FIG. 25, or may be radially expanded by applying an expansion force such as an axially compressive force betweendistal hub 191 andproximal hub 16 or a radial expansion force such as might be applied by an inflatable balloon.Elements 196 may conveniently be formed by laser cutting the same tube stock as utilized to construct thedistal hub 191,proximal hub 16 andframe 14, as will be apparent to those of skill in the art in view of the disclosure herein. Alternatively, the various components of theocclusion device 10 may be separately fabricated or fabricated in subassemblies and secured together during manufacturing. - As a post implantation step for any of the occlusion devices disclosed herein, a radiopaque dye or other visualizable media may be introduced on one side or the other of the occlusion device, to permit visualization of any escaped blood or other fluid past the occlusion device. For example, in the context of a left atrial appendage application, the occlusion device may be provided with a capillary tube or aperture which permit introduction of a visualizable dye from the deployment catheter through the occlusion device and into the entrapped space on the distal side of the occlusion device. Alternatively, dye may be introduced into the entrapped space distal to the occlusion device such as by advancing a small gauge needle from the deployment catheter through the
barrier 15 on the occlusion device, to introduce dye. - A further embodiment of the
occlusion device 10 is illustrated in FIGS. 26-27. Theocclusion device 10 comprises anocclusion member 11 and a stabilizingmember 194 as in the previous embodiment. In the present embodiment, however, each of thedistal segments 198 inclines radially outwardly in the proximal direction and terminates in aproximal end 204. Theproximal end 204 may be provided with atraumatic configuration, for pressing against, but not penetrating, the wall of the left atrial appendage or other tubular body structure. Three or moredistal segments 198 are preferably provided, and generally anywhere within the range of from about 6 to about 20distal segments 198 may be used. In one embodiment, 9distal segments 198 are provided. In this embodiment, 3 of thedistal segments 198 have an axial length of about 5 mm, and 6 of thedistal segments 198 have an axial length of about 1 cm. Staggering the lengths of theproximal segments 198 may axially elongate the zone in the left atrial appendage against which the proximal ends 204 provide anchoring support for the occlusion device. - The
occlusion device 10 illustrated in FIGS. 26 and 27 is additionally provided with ahinge 206 to allow the longitudinal axis of theocclusion member 11 to be angularly oriented with respect to the longitudinal axis of the stabilizingmember 194. In the illustrated embodiment, thehinge 206 is a helical coil, although any of a variety of hinge structures can be utilized. The illustrated embodiment may be conveniently formed by laser cutting a helical slot through a section of the tube from which the principal structural components of theocclusion device 10 are formed. At the distal end of thehinge 206, anannular band 208 connects thehinge 206 to a plurality of axially extendingstruts 210. In the illustratedembodiment 210, threeaxial struts 210 are provided, spaced equilaterally around the circumference of the body. Axial struts 210 may be formed from a portion of the wall of the original tube stock, which portion is left in its original axial orientation following formation of thedistal segments 198 such as by laser cutting from the tubular wall. - The
occlusion member 11 is provided with aproximal zone 212 on each of thespokes 17.Proximal zone 212 has an enhanced degree of flexibility, to accommodate the fit between theocclusion member 11 and the wall of the left atrial appendage.Proximal section 212 may be formed by reducing the cross sectional area of each of thespokes 17, or by increasing the length of each spoke by making a wave pattern as illustrated. - Each of the
spokes 17 terminates in aproximal point 214.Proximal point 214 may be contained within layers of thebarrier 15, or may extend through or beyond thebarrier 15 such as to engage adjacent tissue and assist in retaining theocclusion device 10 at the deployment site. - Referring to FIGS. 28 and 29, a further variation on the
occlusion device 10 illustrated in FIGS. 24 and 25 is provided. Theocclusion device 10 is provided with aproximal face 216 on theocclusion member 11, instead of the open and proximally concave face on the embodiment of FIGS. 24 and 25. Theproximal face 216 is formed by providing aproximal spoke 218 which connects at an apex 220 to eachdistal spoke 17.Proximal spokes 218 are each attached to ahub 222 at theproximal end 192 of theocclusion device 10. Thebarrier 15 may surround either the proximal face or the distal face or both on theocclusion member 11. In general, provision of aproximal spoke 218 connected by an apex 220 to adistal spoke 17 provides a greater radial force than adistal spoke 17 alone, which will provide an increased resistance to compression if theocclusion member 11 is positioned with the LAA. - Referring to FIGS.30-35, an alternate embodiment of the occlusion device in accordance with the present invention is illustrated. In general, the
occlusion device 10 comprises an occluding member but does not include a distinct stabilizing member as has been illustrated in connection with previous embodiments. Any of the embodiments previously disclosed herein may also be constructed using the occluding member only, and omitting the stabilizing member as will be apparent to those of skill in the art in view of the disclosure herein. - The occluding
device 10 comprises aproximal end 192, adistal end 190, and a longitudinal axis extending therebetween. A plurality of supports 228 extend between aproximal hub 222 and adistal hub 191. At least two or three supports 228 are provided, and preferably at least about six. In one embodiment, eight supports 228 are provided. However, the precise number of supports 228 can be modified, depending upon the desired physical properties of theocclusion device 10 as will be apparent to those of skill in the art in view of the disclosure herein, without departing from the present invention. - Each support228 comprises a
proximal spoke portion 218, a distal spoke portion 217, and an apex 220 as has been discussed. However, each of the proximal spoke 218, distal spoke 17 andapex 220 may be a region on an integral support 228, such as a continuous rib or frame member which extends in a generally curved configuration as illustrated with a concavity facing towards the longitudinal axis of theocclusion device 10. Thus, no distinct point or hinge atapex 220 is necessarily provided as is disclosed in previous embodiments, which include a hinged connection between proximal spoke 218 anddistal spoke 17. - At least some of the supports228, and, preferably, each support 228, is provided with one or two or
more barbs 195. In the illustrated configuration, theocclusion device 10 is in its enlarged orientation, such as for occluding a left atrial appendage or other body cavity or lumen. In this orientation, each of thebarbs 195 projects generally radially outwardly from the longitudinal axis, and are inclined in the proximal direction. In an embodiment where thebarbs 195 and corresponding support 228 are cut from a single ribbon, sheet or tube stock, thebarb 195 will incline radially outwardly at approximately a tangent to the curve formed by the support 228. - The
occlusion device 10 illustrated in FIG. 30 may be constructed in any of a variety of ways, as will become apparent to those of skill in the art in view of the disclosure herein. In one preferred method, theocclusion device 10 is constructed by laser cutting a piece of tube stock to provide a plurality of axially extending slots in-between adjacent supports 228. Similarly, eachbarb 195 can be laser cut from the corresponding support 228 or space in-between adjacent supports 228. The generally axially extending slots which separate adjacent supports 228 end a sufficient distance from each of theproximal end 192 anddistal end 190 to leave aproximal hub 222 and adistal hub 191 to which each of the supports 228 will attach. In this manner, an integral cage structure may be formed. Alternatively, each of the components of the cage structure may be separately formed and attached together such as through soldering, heat bonding, adhesives, and other fastening techniques which are known in the art. A further method of manufacturing theocclusion device 10 is to laser cut a slot pattern on a flat sheet of appropriate material, such as a flexible metal or polymer, as has been discussed in connection with previous embodiments. The flat sheet may thereafter be rolled about an axis and opposing edges bonded together to form a tubular structure. - The
apex portion 220 which carries thebarb 195 may be advanced from a low profile orientation in which each of the supports 228 extend generally parallel to the longitudinal axis, to an implanted orientation as illustrated, in which the apex 220 and thebarb 195 are positioned radially outwardly from the longitudinal axis. The support 228 may be biased towards the enlarged orientation, or may be advanced to the enlarged orientation following positioning within the tubular anatomical structure, in any of a variety of manners. For example, referring to FIG. 32, aninflatable balloon 230 is positioned within theocclusion device 10.Inflatable balloon 230 is connected by way of aremovable coupling 232 to aninflation catheter 234.Inflation catheter 234 is provided with an inflation lumen for providing communication between aninflation media source 236 outside of the patient and theballoon 230. Following positioning within the target body lumen, theballoon 230 is inflated, thereby engagingbarbs 195 with the surrounding tissue. Theinflation catheter 234 is thereafter removed, by decoupling theremovable coupling 232, and theinflation catheter 234 is thereafter removed. - In an alternate embodiment, the supports228 are radially enlarged such as through the use of a
deployment catheter 238.Deployment catheter 238 comprises a lumen for movably receiving adeployment line 240.Deployment line 240 extends in aloop 244 formed by aslip knot 242. As will be apparent from FIG. 33, proximal retraction on thedeployment line 240 will cause thedistal hub 191 to be drawn towards theproximal hub 222, thereby radially enlarging the cross-sectional area of theocclusion device 10. Depending upon the material utilized for theocclusion device 10, the supports 228 will retain the radially enlarged orientation by elastic deformation, or may be retained in the enlarged orientation such as by securing theslip knot 242 immovably to thedeployment line 240 at the fully radially enlarged orientation. This may be accomplished in any of a variety of ways, using additional knots, clips, adhesives, or other techniques known in the art. - Referring to FIGS. 34A and 34B, the
occlusion device 10 may be provided with abarrier 15 such as a mesh or fabric as has been previously discussed.Barrier 15 may be provided on only one hemisphere such asproximal face 216, or may be carried by theentire occlusion device 10 fromproximal end 192 todistal end 190. The barrier may be secured to the radially inwardly facing surface of the supports 228, as illustrated in FIG. 34B, or may be provided on the radially outwardly facing surfaces of supports 228, or both. - A further embodiment of the
occlusion device 10 is illustrated in FIG. 35, in which the apex 220 is elongated in an axial direction to provide additional contact area between theocclusion device 10 and the wall of the tubular structure. In this embodiment, one or two or three ormore anchors 195 may be provided on each support 228, depending upon the desired clinical performance. Theocclusion device 10 illustrated in FIG. 35 may also be provided with any of a variety of other features discussed herein, such as a partial orcomplete barrier 15 covering. In addition, theocclusion device 10 illustrated in FIG. 35 may be enlarged using any of the techniques disclosed elsewhere herein. - While particular forms of the invention have been described, it will be apparent that various modifications can be made without departing from the spirit and scope of the invention. Accordingly, it is not intended that the invention be limited, except as by the appended claims.
Claims (48)
Priority Applications (1)
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US10/364,910 US20030220667A1 (en) | 1998-11-06 | 2003-02-11 | Method of containing embolic material in the left atrial appendage |
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Application Number | Priority Date | Filing Date | Title |
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US09/187,200 US6152144A (en) | 1998-11-06 | 1998-11-06 | Method and device for left atrial appendage occlusion |
US09/435,562 US7128073B1 (en) | 1998-11-06 | 1999-11-08 | Method and device for left atrial appendage occlusion |
US10/364,910 US20030220667A1 (en) | 1998-11-06 | 2003-02-11 | Method of containing embolic material in the left atrial appendage |
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US09/435,562 Continuation US7128073B1 (en) | 1998-11-06 | 1999-11-08 | Method and device for left atrial appendage occlusion |
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US09/435,562 Expired - Lifetime US7128073B1 (en) | 1998-11-06 | 1999-11-08 | Method and device for left atrial appendage occlusion |
US10/364,910 Abandoned US20030220667A1 (en) | 1998-11-06 | 2003-02-11 | Method of containing embolic material in the left atrial appendage |
US10/674,553 Expired - Fee Related US8080032B2 (en) | 1998-11-06 | 2003-09-30 | Method and device for left atrial appendage occlusion |
US10/830,964 Abandoned US20050004652A1 (en) | 1998-11-06 | 2004-04-22 | Method for left atrial appendage occlusion |
US11/009,392 Expired - Fee Related US7722641B2 (en) | 1998-11-06 | 2004-12-08 | Filter mesh for preventing passage of embolic material form an atrial appendage |
US11/529,707 Expired - Fee Related US8523897B2 (en) | 1998-11-06 | 2006-09-27 | Device for left atrial appendage occlusion |
US13/109,898 Expired - Fee Related US8535343B2 (en) | 1998-11-06 | 2011-05-17 | Method for left atrial appendage occlusion |
US13/299,796 Expired - Fee Related US8834519B2 (en) | 1998-11-06 | 2011-11-18 | Method and device for left atrial appendage occlusion |
US13/967,081 Expired - Fee Related US9168043B2 (en) | 1998-11-06 | 2013-08-14 | Method for left atrial appendage occlusion |
US14/016,778 Abandoned US20140046360A1 (en) | 1998-11-06 | 2013-09-03 | Device for left atrial appendage occlusion |
US14/922,789 Abandoned US20160106437A1 (en) | 1998-11-06 | 2015-10-26 | Method for left atrial appendage occlusion |
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US09/435,562 Expired - Lifetime US7128073B1 (en) | 1998-11-06 | 1999-11-08 | Method and device for left atrial appendage occlusion |
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US10/674,553 Expired - Fee Related US8080032B2 (en) | 1998-11-06 | 2003-09-30 | Method and device for left atrial appendage occlusion |
US10/830,964 Abandoned US20050004652A1 (en) | 1998-11-06 | 2004-04-22 | Method for left atrial appendage occlusion |
US11/009,392 Expired - Fee Related US7722641B2 (en) | 1998-11-06 | 2004-12-08 | Filter mesh for preventing passage of embolic material form an atrial appendage |
US11/529,707 Expired - Fee Related US8523897B2 (en) | 1998-11-06 | 2006-09-27 | Device for left atrial appendage occlusion |
US13/109,898 Expired - Fee Related US8535343B2 (en) | 1998-11-06 | 2011-05-17 | Method for left atrial appendage occlusion |
US13/299,796 Expired - Fee Related US8834519B2 (en) | 1998-11-06 | 2011-11-18 | Method and device for left atrial appendage occlusion |
US13/967,081 Expired - Fee Related US9168043B2 (en) | 1998-11-06 | 2013-08-14 | Method for left atrial appendage occlusion |
US14/016,778 Abandoned US20140046360A1 (en) | 1998-11-06 | 2013-09-03 | Device for left atrial appendage occlusion |
US14/922,789 Abandoned US20160106437A1 (en) | 1998-11-06 | 2015-10-26 | Method for left atrial appendage occlusion |
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Also Published As
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US20140046360A1 (en) | 2014-02-13 |
US20120065662A1 (en) | 2012-03-15 |
US8523897B2 (en) | 2013-09-03 |
US20130331884A1 (en) | 2013-12-12 |
US20070083227A1 (en) | 2007-04-12 |
US20050004652A1 (en) | 2005-01-06 |
US8080032B2 (en) | 2011-12-20 |
US8535343B2 (en) | 2013-09-17 |
US7722641B2 (en) | 2010-05-25 |
US8834519B2 (en) | 2014-09-16 |
US20040098031A1 (en) | 2004-05-20 |
US9168043B2 (en) | 2015-10-27 |
US20110218566A1 (en) | 2011-09-08 |
US20050203568A1 (en) | 2005-09-15 |
US20160106437A1 (en) | 2016-04-21 |
US7128073B1 (en) | 2006-10-31 |
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