# Patent

## Title
Intraluminal prosthesis attachment systems and methods

## Abstract

Systems and method implant prostheses in the body. The systems and methods provide permanent attachment of the prosthesis in the body. The prosthesis can comprise, e.g., an endovascular graft, which can be deployed without damaging the native blood vessel in either an arterial or a venous system. The endovascular graft can comprise, e.g., a radially expanding vascular stent and/or a stent-graft. The graft can be placed in the vasculature, e.g., to exclude or bridge an aneurysm, for example, an abdominal aortic aneurysms. The graft desirably adapts to changes in aneurysm morphology and repairs the endovascular aneurysm. The fastening systems and methods can be deployed through the vasculature and manipulated from outside the body, to deliver a fastener to attach the graft to the vessel wall.

## Background
RELATED APPLICATION
This application is continuation-in-part of U.S. patent application Ser. No. 10/271,334, filed Oct. 15, 2002, now U.S. Pat. No. 6,960,217, which claims the benefit of U.S. Provisional Application Ser. No. 60/333,937 filed Nov. 28, 2001. The full disclosures of each of these applications are incorporated herein by reference.


BACKGROUND OF THE INVENTION
The invention relates generally to the attachment of a vascular prosthesis to a native vessel, and in particular, to a method and system of devices for the repair of diseased and/or damaged sections of a vessel.
The weakening of a vessel wall from damage or disease can lead to vessel dilatation and the formation of an aneurysm. Left untreated, an aneurysm can grow in size and may eventually rupture.
For example, aneurysms of the aorta primarily occur in abdominal region, usually in the infrarenal area between the renal arteries and the aortic bifurcation. Aneurysms can also occur in the thoracic region between the aortic arch and renal arteries. The rupture of an aortic aneurysm results in massive hemorrhaging and has a high rate of mortality.
Open surgical replacement of a diseased or damaged section of vessel can eliminate the risk of vessel rupture. In this procedure, the diseased or damaged section of vessel is removed and a prosthetic graft, made either in a straight of bifurcated configuration, is installed and then permanently attached and sealed to the ends of the native vessel by suture. The prosthetic grafts for these procedures are usually unsupported woven tubes and are typically made from polyester, ePTFE or other suitable materials. The grafts are longitudinally unsupported so they can accommodate changes in the morphology of the aneurysm and native vessel. However, these procedures require a large surgical incision and have a high rate of morbidity and mortality. In addition, many patients are unsuitable for this type of major surgery due to other co-morbidities.
Endovascular aneurysm repair has been introduced to overcome the problems associated with open surgical repair. The aneurysm is bridged with a vascular prosthesis, which is placed intraluminally. Typically these prosthetic grafts for aortic aneurysms are delivered collapsed on a catheter through the femoral artery. These grafts are usually designed with a fabric material attached to a metallic scaffolding (stent) structure, which expands or is expanded to contact the internal diameter of the vessel. Unlike open surgical aneurysm repair, intraluminally deployed grafts are not sutured to the native vessel, but rely on either barbs extending from the stent, which penetrate into the native vessel during deployment, or the radial expansion force of the stent itself is utilized to hold the graft in position. These graft attachment means do not provide the same level of attachment when compared to suture and can damage the native vessel upon deployment.
SUMMARY OF THE INVENTION
The invention provides systems and methods for implanting prostheses in the body. The systems and methods provide permanent attachment of the prosthesis in the body. The prosthesis can comprise, e.g., an endovascular graft, which can be deployed without damaging the native blood vessel in either an arterial or a venous system. The endovascular graft can comprise, e.g., a radially expanding vascular stent and/or a stent-graft. The graft can be placed in the vasculature, e.g., to exclude or bridge an aneurysm, for example, an abdominal aortic aneurysm. The graft desirably adapts to changes in aneurysm morphology and repairs the endovascular aneurysm. The fastening system and methods are deployed through the vasculature and manipulated from outside the body, to deliver a fastener to attach the graft to the vessel wall.
One aspect of the invention provides a fastener applier for a prosthesis. The applier comprises a drive mechanism sized and configured to be releasably coupled to the fastener to deploy the fastener into the prosthesis. The applier also includes an actuator for the drive mechanism including a sensing mechanism that enables operation of the drive mechanism in response to at least one of (i) a force sensed at or near the fastener, and (ii) contact sensed with a surface at or near the distal end of the fastener body.
Another aspect of the invention provides a fastener sized and configured for deployment in tissue. The fastener includes a fastener body having a distal end for penetrating tissue in response to a force. The fastener body also has a proximal end for releasably coupling the fastener body to a force applier. The fastener includes a stop structure associated with the proximal end to prevent over-penetration of the fastener body into tissue. In one embodiment, the stop structure couples the fastener body to the force applier, e.g., by a magnetic or mechanical coupling. On one embodiment, the fastener body can comprise, e.g., a helical coil.
Another aspect of the invention provides a fastener sized and configured for deployment in tissue. The fastener comprises a fastener body having a distal end for penetrating tissue in response to a force. The fastener body also has a proximal end for releasably coupling the fastener body to a force applier. A tracking wire is coupled to the proximal end to guide the force applier into operative contact with the fastener.
Another aspect of the invention provides a prosthesis comprising a prosthesis body and a fastener assembly integrally carried by the prosthesis body. The fastener assembly includes at least one fastener deployable into tissue in response to force applied by a force applier. A tracking wire is coupled to the fastener to guide the force applier into operative contact with the fastener.
Another aspect of the invention provides a prosthesis comprising a prosthesis body and a fastener assembly integrally carried by the prosthesis body. The assembly includes at least one fastener deployable into tissue in response to non-rotational force applied by a force applier.



BRIEF DESCRIPTION OF THE DRAWINGS
The invention will be understood from the following detailed description of preferred embodiments, taken in conjunction with the accompanying drawings, wherein:
FIG. 1 is a perspective view of one embodiment of an endovascular graft delivery device shown positioned within an abdominal aortic aneurysm;
FIG. 2 is a perspective view of one embodiment the deployment of an endovascular graft within the aneurysm of FIG. 1;
FIG. 3 is a perspective view of a fully deployed straight endovascular graft of FIG. 2;
FIG. 4 is a perspective view of a fully deployed bifurcated endovascular graft broken away to show an anchoring scaffold at one end;
FIG. 5 is a perspective view similar to FIG. 5 showing an alternative scaffold structure;
FIG. 6 is a perspective view showing one embodiment of a device for directing the fastener applier;
FIG. 7 is a perspective view showing the device of FIG. 6 upon insertion within the deployed endovascular graft of FIG. 3 with both the graft and scaffolding broken away;
FIG. 8 is a perspective view of the device of FIG. 6 showing activation of one embodiment of a stabilizing device attached to the directing device;
FIG. 9 is a perspective view of the control assembly in FIG. 8 articulating the directing device of FIG. 6;
FIG. 10 is a perspective view of an alternative embodiment of the stabilization device of FIG. 8;
FIG. 11 is a perspective view showing the activation of the alternative stabilization device of FIG. 10;
FIG. 12 is a perspective view showing another embodiment of the stabilization device of FIG. 8;
FIG. 13 is a perspective view showing activation of the stabilization device of FIG. 12;
FIG. 14 is one embodiment of the fastener applier;
FIG. 14A is an enlarged view of the distal end of the fastener applier shown in FIG. 14, showing the details of the fastener drive mechanism;
FIG. 14B is a section view of the interior of the handle of the fastener applier shown in FIG. 14;
FIG. 15 is a perspective view of the fastener applier of FIG. 14 being positioned within directing device of FIG. 6;
FIG. 16 is an enlarged cross-sectional view of one embodiment of the fastener applier of FIG. 14;
FIG. 17 is an enlarged cross-sectional view of the attachment applier showing one embodiment of the proximal end of the helical fastener and the drive mechanism;
FIG. 18 is a enlarged perspective view of one embodiment of the helical fastener of FIG. 16;
FIG. 19 is an enlarged view of the attachment applier showing one embodiment of the control assembly that activates the fastener applier;
FIG. 20 is an enlarged view of the attachment applied activated with a fastener implanted into the graft and vessel wall;
FIG. 21 is an enlarged view of the completed attachment of the proximal graft of FIG. 3 to the vessel wall with fasteners;
FIG. 22 is a perspective view of the graft of FIG. 4 completely attached to the vessel;
FIG. 23 is an enlarged section view of the drive mechanism of the fastener applier shown in FIG. 14, showing a contact/force sensing assembly that disables the applier in the absence of desired contact between the fastener and a targeted tissue region;
FIG. 24 is an enlarged section view of the drive mechanism of the fastener applier shown in FIG. 14, showing the contact/force sensing assembly enabling use of the applier in response to desired contact between the fastener and the targeted tissue region;
FIGS. 25A and 25B are enlarged views of the distal end of a fastener applier showing the details of an alternative embodiment of the fastener drive mechanism;
FIG. 26A is an enlarged section view of the drive mechanism of the fastener applier shown in FIGS. 25A and 25B showing a contact/force sensing assembly that disables the applier in the absence of desired contact between the fastener and a targeted tissue region;
FIGS. 26B and 26C are enlarged section views of the drive mechanism of the fastener applier shown in FIGS. 25A and 25B, showing the contact/force sensing assembly enabling use of the applier in response to desired contact between the fastener and the targeted tissue region;
FIG. 27 is a perspective view of a helical fastener that can be used in association with the fastener applier shown in FIGS. 14, 23, and 24;
FIG. 28A is a perspective view of a helical fastener that can be used in association with the fastener applier shown in FIGS. 25A and 25B;
FIG. 28B is perspective view of a helical fastener that can be used in association with the fastener applier shown in FIGS. 26A to 26C;
FIG. 29 is an enlarged side view, partially in section, of a fastener applier having an angled applicator end that can be used to deploy the helical fastener shown in FIG. 27 without use of a separate directing device;
FIG. 30 is an enlarged side view, partially in section, of an alternative embodiment of an angled fastener applier that can be used to deploy the helical fastener shown in FIG. 27 without use of a separate directing device;
FIG. 31 is an enlarged side view, partially in section, of an alternative embodiment of an angled fastener applier that can be used to deploy the helical fastener shown in FIG. 27 without use of a separate directing device, the fastener applier having an articulating applicator end;
FIG. 32 is a perspective view of an endovascular prosthesis shown positioned within an abdominal aortic aneurysm, the prosthesis including an integrated fastener assembly;
FIG. 33 is a perspective view of the endovascular prosthesis shown in FIG. 32, with an intraluminal tool deployed to operatively interact with the integrated fastener assembly, to temporarily or permanently anchor the prosthesis to the wall of the vessel;
FIG. 34 is a side view of a fastener that forms a part of the integrated fastener assembly shown in FIG. 33, the fastener having a stem, which is shown in a normally spread-apart condition before its association with the integrated fastener assembly;
FIG. 35 is a side view of the fastener shown in FIG. 34, the fastener stem now being shown in a closed condition and housed within a grommet that forms a part of the integrated fastener assembly;
FIGS. 36 and 37 are side views showing the use of the intraluminal tool shown in FIG. 33 to apply force to drive the fastener from its position shown in FIG. 35 and through the vessel wall;
FIG. 38 is the integrated fastener assembly after deployment to anchor a prosthesis to a vessel wall;
FIG. 39 is a side view showing the use of a tracking wire to guide a intraluminal tool into contact with a fastener, so that force can be applied to drive the fastener through the vessel wall;
FIG. 40 is an embodiment of a prosthesis delivery catheter for a prostheses in which the stent structure covers only a portion of the prosthesis, the catheter including an array of stabilization struts to help hold the prosthesis in position against the flow of blood;
FIG. 41 is another embodiment of a prosthesis delivery catheter for a prostheses in which the stent structure covers only a portion of the prosthesis, the catheter including an array of inverted stabilization struts to help hold the prosthesis in position against the flow of blood; and
FIG. 42 is another embodiment of a prosthesis delivery catheter for a prostheses in which the stent structure covers only a portion of the prosthesis, the catheter including a stabilization basket to help hold the prosthesis in position against the flow of blood.



DETAILED DESCRIPTION OF THE INVENTION
I. Delivering a Prosthesis
FIG. 1 depicts an endovascular graft delivery catheter 10 as it is being positioned over a guidewire 12 in a body lumen. The catheter 10 carries a prosthesis 14 (see FIG. 2), which is placed at a targeted site, e.g., by radial expansion of the prosthesis 14 (see FIG. 3). After expansion of the prosthesis 14, one or more fasteners 28 (see FIGS. 15 and 16) are introduced by a fastener attachment assembly to anchor the prosthesis 14 in place.
For the purposes of illustration, FIG. 1 shows the targeted site as being within an abdominal aortic aneurysm 11. The targeted site can be elsewhere in the body. In the illustrated arrangement, the prosthesis 14 takes the form of an endovascular graft.
FIG. 2 depicts the initial stage of graft deployment at the targeted site. While the deployment method can vary, in the illustrated embodiment, the delivery catheter 10 has a movable cover 13, which overlays the graft 14. When the cover 13 is pulled proximally, the graft 14 is free to radially expand, thereby enlarging to contact the internal walls of the blood vessel. The graft 14 is shown to be self-expanding. Alternatively, the graft 14 can utilize an expanding member, such as a balloon or mechanical expander.
The process of graft deployment is continued, until the graft 14 is fully deployed within the vessel. The graft 14 can be sized and configured to be either straight or bifurcated form. FIG. 3 depicts a completely deployed straight graft 14. FIG. 4 depicts a completely deployed bifurcated graft 15.
A. The Prosthesis
The graft 14 desirably incorporates a support frame or scaffold 16. The scaffold 16 may be elastic, e.g., comprised of a shape memory alloy elastic stainless steel, or the like. For elastic scaffolds, expanding typically comprises releasing the scaffolding from a constraint to permit the scaffold to self-expand at the implantation site. In the illustrated arrangement, the cover 13 serves as a radial constraint. Alternatively, placement of a tubular catheter, delivery sheath, or the like over the scaffold 16 can serve to maintain the scaffold in a radially reduced configuration. In this arrangement, self-expansion of the scaffold 16 is achieved by pulling back on the radial constraining member, to permit the scaffold 16 to assume its larger diameter configuration.
Alternatively, the scaffold 16 may be constrained in an axially elongated configuration, e.g., by attaching either end of the scaffold to an internal tube, rod, catheter or the like. This maintains the scaffold 16 in the elongated, reduced diameter configuration. The scaffold 16 may then be released from such axial constraint in order to permit self-expansion.
Alternatively, the scaffold 16 may be formed from a malleable material, such as malleable stainless steel of other metals. Expansion may then comprise applying a radially expansive force within the scaffold to cause expansion, e.g., inflating a scaffold delivery catheter within the scaffold in order to affect the expansion. In this arrangement, the positioning and deployment of the endograft can be accomplished by the use of an expansion means either separate or incorporated into the deployment catheter. This will allow the endograft to be positioned within the vessel and partially deployed while checking relative position within the vessel. The expansion can be accomplished either via a balloon or mechanical expansion device. Additionally, this expansion stabilizes the position of the endograft within the artery by resisting the force of blood on the endograft until the endograft can be fully deployed.
The graft 14 may have a wide variety of conventional configurations. It can typically comprise a fabric or some other blood semi-impermeable flexible barrier which is supported by the scaffold 16, which can take the form of a stent structure. The stent structure can have any conventional stent configuration, such as zigzag, serpentine, expanding diamond, or combinations thereof. The stent structure may extend the entire length of the graft, and in some instances can be longer than the fabric components of the graft. Alternatively, the stent structure can cover only a small portion of the prosthesis, e.g., being present at the ends. The stent structure may have three or more ends when it is configured to treat bifurcated vascular regions, such as the treatment of abdominal aortic aneurysms, when the stent graft extends into the iliac arteries. In certain instances, the stent structures can be spaced apart along the entire length, or at least a major portion of the entire length, of the stent-graft, where individual stent structures are not connected to each other directly, but rather connected to the fabric or other flexible component of the graft.
One illustrative embodiment of the graft scaffold 16 or stent structure is illustrated in the area broke away in FIG. 4. Here, the stent structure is in the form of a simple zigzag pattern, however it is contemplated that the stent design could involve more complex patterns 17 as depicted in FIG. 5. Although only one stent structure within the graft is depicted, in FIGS. 4 and 5, it is contemplated that multiple independent stent structures could be incorporated into the graft, as previously described.
FIG. 40 shows an embodiment of a prosthesis delivery catheter 600 for a prostheses 14 in which the stent structure 16 covers only a portion of the prosthesis, e.g., being present only at the ends. As shown in FIG. 40, the prosthesis delivery catheter 600 (which is shown deployed over a guidewire 610) includes an array of stabilization struts 612 that are releasably coupled to the stent structure 16 at the end of the prosthesis 14, e.g., by sutures that can be released by pulling on a drawstring (not shown) that passes through a lumen in the catheter 600. The stabilization struts 612 hold the self-expanding stent structure 16 in position against the vessel wall 34, while the remainder of the prosthesis 14 is being deployed (by withdrawal of a delivery sheath 614). The struts 612 support the stent structure 16 (and thus the overall prosthesis 14) against the force of blood flow through the vessel during prosthesis deployment. The catheter 600 can also include a nose cone 618 at its distal end to diffuse blood flow toward the vessel wall, to aid in supporting the prosthesis 14 during its deployment. Upon, deployment of the prosthesis 14, the struts 612 can be detached from the stent structure 14 by pulling upon the drawstring to release the sutures, and the catheter 600 is withdrawn over the guidewire 610 through the delivery sheath 614 (the struts 612, freed from the stent structure 16, fold back upon the catheter 600 during passage through the delivery sheath 614).
FIG. 41 shows an alternative embodiment of a prosthesis delivery catheter 700 for a prostheses 14 in which the stent structure 16 covers only a portion of the prosthesis, e.g., being present at the ends. As shown in FIG. 40, the prosthesis delivery catheter 700 (which is also shown deployed over a guidewire 710) includes an array of inverted stabilization struts 712 that are releasably coupled to the stent structure 16 at the end of the prosthesis 14, e.g., by sutures that can be released by pulling on a drawstring (not shown) that passes through a lumen in the catheter 700. The inverted stabilization struts 712, like the struts 612 shown in FIG. 40, hold the self-expanding stent structure 16 in position against the vessel wall 34, while the remainder of the prosthesis 14 is being deployed (by withdrawal of a delivery sheath 714). Like the catheter 600 in FIG. 40, the catheter 700 can also include a nose cone 718 at its distal end to diffuse blood flow toward the vessel wall. Upon, deployment of the prosthesis 14, the struts 712 are detached from the stent structure 14 by pulling upon the drawstring not shown), and the catheter 700 is withdrawn over the guidewire 710 through the delivery sheath 714 (the struts 612, freed from the stent structure 16, fold back upon the catheter 600 during passage through the delivery sheath 614).
FIG. 42 shows another alternative embodiment of a prosthesis delivery catheter 800 for a prostheses 14 in which the stent structure 16 covers only a portion of the prosthesis, e.g., being present at the ends. As shown in FIG. 42, the prosthesis delivery catheter 800 (which is also shown deployed over a guidewire 810) includes a self-expanding stabilization basket 812. The stabilization basket 812 holds the self-expanding stent structure 16 in position against the vessel wall, while the remainder of the prosthesis 14 is being deployed (by withdrawal of a delivery sheath 814). Like the catheters 600 and 700 in FIGS. 40 and 41, the catheter 800 can also include a nose cone 818 at its distal end to diffuse blood flow toward the vessel wall. Upon, deployment of the prosthesis 14, the stabilization basket is placed into a collapsed condition by withdrawal through the delivery sheath 814, as the catheter 800 is withdrawn over the guidewire 810.
In all of the just-described embodiments, the guidewire 610, 710, 810 can be subsequently used to deploy a fastener attachment assembly for the prosthesis 14, as will be described in greater detail next.
II. Fastening the Prosthesis
In a desired embodiment, a fastener attachment assembly is provided that makes possible intraluminal fastener attachment. The attachment assembly can be variously constructed.
A. Two Component Fastener Guide and Attachment Assembly
In one arrangement, the fastener attachment assembly comprises a fastener guide or directing component 18 and a fastener applier component 27. The guide component 18 desirably has a steerable or deflectable distal tip, which is initially deployed over the guidewire 12. In use, the guidewire 12 that is used to deliver and position the prosthesis 14 desirably remains within the vessel for subsequent deployment of the fastener guide component 18.
Optionally, the guide component 18 includes a stabilizer for holding, following removal of the guidewire 12, the deflected tip against a location in the prosthesis 14, to which a fastener 28 for the prosthesis 14 is to be applied.
In this arrangement, the applier component 27 is desirably deployed through the guide component 18. The fastener applier 27 carries at least one fastener 28 and a fastener drive mechanism 100 for advancing the fastener 28, so that it penetrates the prosthesis 14 and underlying vessel wall, to thereby anchor the prosthesis 14 firmly in place.
1. Fastener Directing Component
FIG. 6 depicts one embodiment of the directing or guide component 18 that forms a part of the fastener attachment assembly. The component 18 takes the form of a directing device 18. The device 18 has an obturator 19 positioned within a lumen of the directing device 18, which extends past the distal of the tip of the directing device. The obturator 19 has a lumen to allow for delivery of the directing device 18 over the guidewire 12, as shown in FIG. 7.
The directing device 18 desirably includes an integrated stabilizing device 20, which aids in maintaining position of the directing device 18 within the vessel upon removal of the guidewire 12. In one embodiment, the stabilizing device 20 is spring-loaded and is positioned for deployment when the obturator 19 and guidewire 12 are removed (see FIG. 8).
In the illustrated embodiment (see FIG. 8), the directing device 18 includes a control assembly 21. In one embodiment the control assembly 21 features a movable wheel or lever 22, which operate interior steering wires in a conventional fashion to deflect the distal tip 23 of the directing device 18 toward a desired location, as seen in FIG. 9. It is contemplated that the control assembly for the directing device 18 could be activated mechanically, electrically, hydraulically or pneumatically. The control assembly 21 has a through lumen to allow for the passage of the obturator 19 and applier component 27.
FIG. 10 depicts an alternative embodiment, in which the stabilizing device 20 takes the form of a movable strut assembly 24. The movable strut assembly 24 can be activated, e.g., through a lever 25 on the control assembly (see FIG. 11). In both embodiments (FIGS. 7 and 10) the stabilizing device 20 is distal to the end of the directing device.
In another alternative embodiment (see FIG. 12), the stabilizing device 20 takes the form of an expandable member 26 adjacent to the distal tip of the directing device. As shown in FIG. 13, the expandable member 26 can be activated, e.g., through a lever 25 on the control assembly 21. However it also contemplated that this type of stabilizing device 20 could also be inflatable. In all embodiments the stabilizing device could be use to stabilize the directing device 18 either concentrically or eccentrically within the vessel.
In another embodiment, a separate stabilization device could be used in cooperation with the directing device 18 and to access the vessel. This separate stabilization device could incorporate the forms of the stabilizing devices described above, or some other form of stabilization mechanism.
2. Fastener Applier Component
FIG. 14 shows one embodiment of the applier component 27 that forms a part of the fastener attachment assembly. The component 27 takes the form of a fastener applier 27. FIG. 15 depicts the fastener applier 27 being deployed through a lumen of the directing device 18 to the site where a fastener 28 will be installed.
Located at the distal end of the fastener applier 27 (see FIG. 14) is a fastener drive mechanism 100. In the illustrated embodiment (see FIG. 14A), the drive mechanism 100 includes a driver 29 that is coupled to a carrier 102. The coupling between the driver 29 and carrier 102 can take different forms—e.g., magnets, graspers, or other suitable mechanical connection. In the embodiment illustrated in FIG. 14A, the driver 29 and carrier 102 are integrally connected as a single unit.
The carrier 102 is sized and configured to engage a selected fastener 28. In FIG. 14A, the fastener takes the form of a helical fastener of the type shown in FIGS. 18 and 27. As best shown in FIG. 27, and as will be described in greater detail later, the helical fastener 28 in FIG. 26 is an open coil 148 with a sharpened leading tip 142. The proximal end 144 of the fastener 28 includes an L-shaped leg 146. The L-shape leg 146 desirably bisects the entire interior diameter of the coil 148; that is, the L-shaped leg 146 extends completely across the interior diameter of the coil 148, as FIG. 27 shows. The L-shaped leg 146 serves to engage the carrier 102 of the fastener applier 27, which rotates the helical fastener to achieve implantation. The L-shaped leg 146 also serves as a stop to prevent the helical fastener from penetrating too far into the tissue.
The carrier 102 in FIG. 14A includes a slot 180, which receives the L-shaped leg 146 to couple the fastener 28 for rotation with the carrier 102. The turns of the coil 148 rest in complementary internal grooves 32 that surround the carrier 102. The grooves 32 could be positioned along the entire length of the fastener 28 or within a portion of its length.
The actuation of the drive mechanism 100 can, of course, be accomplished in various ways, e.g., mechanical (i.e., manual or hand-powered), electrical, hydraulic, or pneumatic. In the illustrated embodiment (see FIG. 14B), a drive cable 30 couples the fastener driver 29 to an electric motor 106 carried in the applier handle 108. The drive cable 30 is desirably made of a suitable material that allows for both bending and rotation. Driven by the motor 106 (which is, in turn, under the control of motor control unit 31, as will be described later), the drive cable 30 rotates the driver 29 and, with it, the carrier 102. The carrier 102 imparts rotation and torque to the helical fastener 28 for implantation in tissue.
FIG. 16 is an enlarged cross-sectional view of fastener applier 27 and directing device 18. FIG. 17 is an enlarged cross-sectional view of the fastener applier 27 with a cross-section of the fastener driver 29 depicting the engagement between the fastener driver 29 and helical fastener 28. FIG. 19 depicts the fastener applier 27 during activation of the fastener drive mechanism 100. Activation of the drive mechanism 100 rotates, as a unit, the drive shaft 30, the driver 29, the carrier 102, and helical fastener 28. This rotation causes the helical fastener 28 to travel within the internal grooves 32 of the fastener applier and into the prosthesis 14 and vessel wall 34 (see FIG. 20). FIG. 21 illustrates a completed helical fastener 28 attachment of the graft 14 to the vessel wall 34.
In use, the applier 27 is advanced through the directing device 18 and into contact with the prosthesis. The operator actuates the control unit 31 by contacting a control switch 110 (see FIGS. 14 and 14B). This action causes the helical fastener 28 to be rotated off the carrier 102 and through the prosthesis 14 and into the vessel wall 34. The motor control unit 31 desirably rotates the drive cable 30 a specific number of revolutions with each activation command. This can be accomplished by incorporating a mechanical or electrical counter.
With the deployment of a fastener 28, the applier 27 is retrieved through the directing device 18, and another fastener 28 is loaded into the carrier 102. The directing device 18 is repositioned and stabilized, and the applier 27 is advanced again through the directing device 18 and into contact with the prosthesis 14. The operator again actuates the control unit 31 by contacting the control switch 110 to deploy another fastener 28. This process is repeated at both proximal and/or distal ends of the prosthesis 14 until the prosthesis 14 is suitably attached and sealed to the vessel wall 34. It is contemplated that from about two to about twelve fasteners 28 may be applied at each end of the prosthesis 14 to affect anchorage. The fasteners 28 can be applied in a single circumferentially space-apart row, or may be applied in more than one row with individual fasteners being axially aligned or circumferentially staggered.
FIG. 22 illustrates a perspective view of a graft prosthesis attached to the vessel wall both proximally and distally. It is contemplated that the present invention can be used for graft attachment of both straight and bifurcated grafts within the aorta and other branch vessels.
An alternative embodiment of the drive mechanism 100 is shown in FIGS. 25A and 25B. In this embodiment, the driver 29 is coupled to a carrier 150, which forms a part of the helical fastener 28 itself, as also shown in FIG. 28A. As shown in FIG. 28A, the helical fastener 28 is, like the fastener shown in FIG. 27, an open coil 148 with a sharpened leading tip 142. The proximal end 144 of the fastener 28 includes the carrier 150.
The carrier 150 includes a slot 182. The slot 182 engages a drive flange 184 on the driver 29 (see FIG. 25A) to impart rotation of the driver 29 to rotation of the helical fastener 28 during the implantation process. Like the L-shaped leg of the fastener shown in FIG. 27, the carrier 150 also serves as a stop to prevent the helical fastener from penetrating too far into the tissue.
The coupling engagement between the carrier 150 and the driver 29 could be accomplished in various ways, e.g., by separate graspers or grippers, a magnetic couple, or any other suitable mechanical connecting means. In the illustrated embodiment, the driver 29 is made of a magnetized material, and the carrier 150 is made from a material that is magnetically attracted toward the magnetized material. Of course, a reverse arrangement of magnetized and magnetically attracted materials could be used.
In this arrangement, the motor coupling 132 between the drive cable 30 and the motor 106 accommodates axial displacement of the motor cable 30 (left and right in FIGS. 25A and 25B) without interrupting the drive connection with the motor 106. With the distal tip of the applier device 27 in contact with the prosthesis 14 (see FIG. 25A), the operator actuates the control unit 31 by contacting a control switch 110. The control unit 31 commands the motor 106 to rotate the drive cable 30 to impart rotation to the driver 29 and the magnetically attached helical fastener 28. This action causes the magnetically attached helical fastener 28 to be rotated into prosthesis 14 and the vessel wall 34 (see FIG. 25B). Due to the magnetic coupling, as the fastener 28 is deployed to the left in FIG. 25B, the driver 29 moves in tandem with carrier 150 (also to the left in FIG. 25B). Due to the magnetic coupling between the carrier 150 and the driver 29, the operator must exert a deliberate separation force to decouple the carrier 150 (and, with it, the fastener 28) from the driver 29. This arrangement prevents inadvertent release of a fastener 28.
As before described, with the deployment of a fastener 28, the applier 27 is retrieved through the directing device 18, and another fastener 28 is magnetically coupled to the driver 29. The directing device 18 is repositioned and stabilized, and the applier 27 is advanced again through the directing device 18 and into contact with the prosthesis 14. The operator again actuates the control unit 31 by contacting a control switch 110 to deploy another fastener 28. This process is repeated at both proximal and/or distal ends of the prosthesis 14 until the prosthesis 14 is suitably attached and sealed to the vessel wall 34.
As indicated in the above description, the outer diameter of the applier component 27 is desirably sized and configured to pass through the lumen of the directing component 18, which can take the form of a suitable steerable guide catheter, to direct the applier component 27 to the desired location. As also above described, the applier component 27 is desirably configured to implant one fastener 28 at a time (a so-called “single fire” approach). This is believed desirable, because it reduces the complexity of the design and accommodates access of the applier 27 through tortuous anatomy. Fastener appliers 27 which carry a single fastener can have a lower profile and may be more effective and less traumatic than fastener appliers which carry multiple fasteners. Still, in alternative embodiments, the applier component 27 may, if desired, be configured to carry multiple fasteners. Moreover, the fastener applier 27 may simultaneously deploy multiple fasteners in the preferred circumferentially spaced-apart space pattern described above.
a. Prosthesis/Tissue Contact Sensing
The fastener applier 27 desirably incorporates a function that prevents actuation of the motor 106 until the tip of the applier 27 is in a desired degree of contact with the prosthesis or tissue surface. This prevents inadvertent discharge of a fastener 28 and/or separation of the fastener 28. This function can be implemented, e.g., using a contact or force sensor, which is either mechanical or electrical in design.
When the fastener applier 27 is of the type shown in FIGS. 14A. 14B, and 14C (see FIGS. 23 and 24), the contact or force sensing function can, e.g., utilize the distal tip 120 of the carrier 102 to transmit a contact force. This force can be transmitted to a force or contact sensing switch 122 located, e.g., within the fastener applier handle 108. In this arrangement, the switch 122 can be part of the electrical circuit between the actuator switch 110 and the control unit 31.
In the illustrated embodiment, the switch 122 includes a stationary switch element 128 (coupled to the interior of the handle 108) and a movable switch element 130 (carried by the drive cable 31). In this arrangement, the motor coupling 132 between the drive cable 30 and the motor 106 accommodates axial displacement of the motor cable 30 (left and right in FIGS. 23 and 24) without interrupting the drive connection with the motor 106. The drive cable 30 is coupled by a bearing 134 to the movable switch element 130, so that the switch element 130 moves in response to movement of the drive cable 30. The stationary switch element 128 is not coupled to the movable drive cable 30, which slidably passes through the switch element 130.
Due to this arrangement, axial displacement of the drive cable 30 moves the switch element 130 relative to the switch element 128. More particularly, displacement of the drive cable 30 to the left in FIG. 23 moves the switch element 130 to the left, away from the switch element 128. Conversely, displacement of the drive cable 30 to the right in FIG. 23 moves the switch element 130 to the right, toward the switch element 128.
A spring 126 normally biases the switch elements 128 and 130 apart, comprising an electrically opened condition. In this condition, operation of the actuating switch 110 does not serve to actuate the control unit 31, as the electrically open switch 122 interrupts conveyance of the actuation signal to the motor control unit 31. When the switch elements 128 and 130 are in the electrically opened condition, the drive cable 30 is displaced to the left to position the carrier tip 120 beyond the distal tip 124 of the fastener applier 27. The carrier tip 120 therefore makes contact with the prosthesis 14 or tissue in advance of the applier tip 124.
When the carrier tip 120 contacts the surface of the prosthesis or tissue with sufficient force to compress the spring 126, the drive cable 30 is displaced against the biasing force of the spring to the right in FIG. 23. This moves the switch element 130 to the right. Ultimately, contact between the switch elements 128 and 130 will occur, as shown in FIG. 24. The contact establishes an electrically closed condition. In this condition, operation of the actuating switch 110 serves to actuate the control unit 31. As shown in FIGS. 23 and 24, a contact screw 136 can be provided to adjust the amount of displacement required to close the switch elements 128 and 130.
Upon removal of contact force, or in the absence of sufficient contact force, the spring 126 urges the switch elements 128 and 130 toward the electrically opened condition. The distal tip of the carrier 102 is located distally beyond the distal tip of the applier 27.
It should be appreciated that the translation of movement of the carrier tip 120 to the switch 122 need not occur along the entire length of the drive cable 30. For example, the switch 122 can be located in a translation space between the carrier 102 and the driver 29. In this arrangement, the driver 29, coupled to the drive cable 30 need not accommodate axial displacement. Instead, relative movement of the carrier 102 toward the driver 29 in response to contact with the prosthesis 14 will mechanically couple the carrier 10 with the driver 29 (e.g., through a slot and flange connection similar to that shown in FIGS. 25A and 25B), while also closing the switch 122 to energize the circuit between the actuator switch 110 and the motor control unit 31.
When the fastener applier 27 is of the type shown in FIGS. 25A and 25B (see FIGS. 26A, 26B, and 26C), the contact or force sensing function can, e.g., utilize a force sensing rod 190 that slidably passes through a central passage 192 in the carrier 150′ (the carrier 150′ is shown in FIG. 28B), the driver 29 and the drive cable 30. The rod 190 is coupled to the movable switch element 130. In this embodiment, the switch element 130 translates left and right over the drive cable 30, which rotates on a bearing 134 within the switch element 130.
As in the preceding embodiment, the spring 126 normally biases the switch elements 128 and 130 apart, comprising an electrically opened condition. When the switch elements 128 and 130 are in the electrically opened condition, the force sensing rod 190 is displaced to the left beyond the distal tip 124 of the fastener applier 27. The force sensing rod 190 therefore makes contact with the prosthesis 14 or scaffold structure 16 in advance of the applier tip 124.
When the rod 190 contacts the surface of the prosthesis or scaffold structure with sufficient force to compress the spring 126, the rod 190 is displaced against the biasing force of the spring 126 to the right in FIG. 26A. This moves the switch element 130 to the right. Ultimately, contact between the switch elements 128 and 130 will occur, as shown in FIG. 26B. The contact establishes an electrically closed condition. In this condition, operation of the actuating switch 110 serves to actuate the control unit 31. This action causes the helical fastener 28 to be rotated into the scaffold structure 16 and into the vessel wall 34 (see FIG. 26C). Due to the magnetic coupling between the driver 29 and carrier 150′, the driver 29 is moved in tandem with attached carrier 150′ to the left in FIG. 26B, as the fastener 28 is deployed. Also, due to the magnetic coupling between the carrier 150 and the driver 29, the operator must exert a separation force to decouple the carrier 150 (and, with it, the fastener 28) from the driver 29. As before described, this arrangement prevents inadvertent release of a fastener 28. A contact screw 136 can be provided to adjust the amount of displacement required to close the switch elements 128 and 130.
Upon removal of contact force, or in the absence of sufficient contact force, the spring 126 urges the switch elements 128 and 130 toward the electrically opened condition, moving the tip of the rod 190 out beyond the distal tip 124 of the applier 27.
The contact or force sensing arrangements just described can also generate an audible and/or visual output to the operator, to indicate that sufficient contact force between the applier device 27 and the prosthesis or tissue exists.
B. Angled Component Fastener Guide and Attachment Assembly
In another arrangement (see FIG. 29), the fastener attachment assembly comprises a unitary, angled fastener guide and applier component 160. In this arrangement, the component 160 includes a fastener drive mechanism 162 that places the carrier 164 holding the fastener 28 in a perpendicular or near perpendicular position with respect to the prosthesis or tissue. This configuration eliminates the need for a separate steerable guide component 18 for the fastener component 27, previously described.
The drive mechanism 162 can vary. In the illustrated embodiment (shown in FIG. 29), the mechanism 162 includes a beveled drive gear 168 coupled to the drive cable 30. The drive gear 168 operatively meshes with a transfer or pinion gear 170, which is coupled to the carrier 164. The axes of rotation of the drive gear 168 and pinion gear 170 are offset about ninety degrees, so that rotation of the drive cable 30 along the axis of the vessel is translated into rotation of the carrier 164 generally perpendicular to the wall of the vessel. The fastener guide and applier component 160 can be positioned and stabilized within the vessel in various ways, e.g., through the use external spring loaded strut or the like (as shown in association with the directing component 18 discussed above), or by use of an expandable member 166 (as FIG. 29 shows). The expansion member 166 can comprise either a balloon or mechanical expansion device. The expansion member 166 stabilizes the position of both the prosthesis and the fastener guide and applier component 160 within the vessel by resisting the force of blood until the prosthesis can be anchored.
As FIG. 30 shows, the fastener guide and applier component 160 can, if desired, provide an angled deployment between the drive cable 30 and carrier 164 that is somewhat less than ninety-degrees, to aid in intraluminal manipulation of the carrier into perpendicular contact position against the wall of the vessel. As FIG. 31 shows, the fastener guide and applier component 160 can, if desired, be articulated between the drive cable 30 and carrier 164. In this arrangement, a remote control mechanism is desirable provided to move the carrier 164 from a first, generally straight position (shown in phantom lines in FIG. 31) for deployment to the targeted site, to a second, articulated position (shown in solid lines in FIG. 31) for alignment of the carrier 164 in contact against the vessel wall.
III. The Fasteners
As illustrated and described thus far, introduction of the fasteners 28 will typically be affected after the prosthesis 14 has been initially placed. That is, initial placement of the prosthesis 14 will be achieved by self-expansion or balloon expansion, after which the prosthesis 14 is secured or anchored in place by the introduction of a plurality of individual fasteners. The fasteners 28 may be placed only through the fabric of the prosthesis 14, i.e., avoiding the scaffold structure. Alternately, the fasteners 28 can be introduced into and through portions of the scaffold structure itself. The prosthesis 14 may include preformed receptacles, apertures, or grommets, which are specially configured to receive the fasteners. The fasteners 28 may be introduced both through the fabric and through the scaffold structure. The fasteners can be introduced singly, i.e., one at a time, in a circumferentially spaced-apart pattern over an interior wall of the prosthesis 14.
In the exemplary embodiment, the fasteners 28 are helical fasteners, so that they can be rotated and “screwed into” the prosthesis 14 and vessel wall. A desired configuration for the helical fastener 28 (see FIGS. 27, 28A, and 28B) is an open coil 148, much like a coil spring. This configuration allows the fastener 28 to capture a large area of tissue, which results in significantly greater holding force than conventional staples, without applying tissue compression, which can lead to tissue necrosis.
As FIGS. 27, 28A, and 28B show, the leading tip 142 of the helical fastener 28 is desirable sharp to allow it to penetrate thought the artery wall and/or calcified tissue. This distal tip 142 can be sharpened to cut a helical path through the tissue or it can be sharpened to a point to penetrate the tissue without cutting.
The proximal end 144 of the fastener serves two design functions. The first function is to engage the carrier 102 of the fastener applier 27, which rotates the helical fastener during the implantation process. The second function is to act as a stop to prevent the helical fastener from penetrating too far into the tissue.
In one embodiment (see FIG. 27), the proximal end 144 of the helical fastener 28 includes an L-shaped leg 146 of the coil 148 bisecting the fastener diameter. The leg 146 of the coil 148 comes completely across the diameter to prevent the fastener from being an open coil and to control the depth of penetration into the tissue. In addition, the leg 146 of the coil 148 can be attached to a previous coil to strengthen the entire structure and provide a more stable drive attachment point for the fastener applier. This attachment could be achieved via welding, adhesive or any other suitable means.
Alternatively (as shown in FIGS. 28A and 28B), the proximal end 144 of the fastener 28 could incorporate a separate cap or carrier 150 or 150′ that serves the same function as the leg 146 of the coil 148 in FIG. 27. The carrier 150 or 150′ could feature several methods to attach to the fastener applier drive mechanism 100. These include separate graspers or grippers, a magnetic couple (as previously described), or any other suitable mechanical connecting means. In FIGS. 28A and 28B, the carrier 150 and 150′ includes a slot 180 and 182′ to mate with a drive flange (as previously described). As also previously described, a magnetic coupling is implemented between the carrier 150 and 150′ and the corresponding drive member, to prevent inadvertent separation during use.
In FIG. 28B, the carrier 150′ also includes a passage 152 for holding the contact/force sensing rod 190 shown in FIGS. 26A, 26B, and 26C.
The fasteners 28 shown in FIGS. 27, 28A, and 28B can be made from stainless steel or other types of implantable metal, however it is also envisioned that the fasteners in the above descriptions could be made from implantable polymers or from a biodegradable polymer or combinations of all materials thereof. Desirably, a fastener 28 will have between 2 and 10 turns and will be between 1 mm and 10 mm long. The space between the individual coils will be between 0.25 mm and 3 mm. The diameter of the fastener 28 will be between 1 mm and 6 mm.
IV. Prosthesis with Integrated Fastener Assembly
FIG. 32 shows a prosthesis 500 that includes at least one integrated fastener assembly 502. FIG. 32 shows the prosthesis 500 deployed in a targeted intraluminal region, in particular, within an abdominal aortic aneurysm 504. The prosthesis 500 can be deployed elsewhere in the body.
The prosthesis 500 desirably includes a fabric material or the like carried by a support frame or scaffold 504, as previously described. The scaffold 504 can be made, e.g., from an elastic material that self-expands radially during deployment from a sheath, or from a malleable material that expands radially in response to a radially expansive force applied within the scaffold by a balloon or a mechanical expansion device.
Following deployment of the prosthesis 500 in the targeted region, the integrated fastener assembly 502 on the prosthesis 500 is manipulated to anchor the prosthesis 500 to the vessel wall. In the illustrated embodiment, the prosthesis 500 carries two integrated fastener assemblies 502, one in each end region of the prosthesis 500.
In the illustrated embodiment, each fastener assembly 502 is imbedded in a reinforced flange area 506 in the respective end region. Each fastener assembly 502 comprises an array of fasteners 508 circumferentially spaced about the flange 506. The number of fasteners 508 in the array can vary, e.g., from about two to about twelve fasteners on each flange area 506. The configuration of the array can also vary, e.g., in the circumferential array, the fasteners 508 can by axially spaced apart as well.
The fasteners 508 can be formed of a metal or plastic material and can be variously constructed. In the illustrated embodiment, each fastener 508 includes a disc-shaped head 512 and a stem 514 that is bifurcated into two wings 516 and 518, which are joined by a plastic or memory material hinge region 520. The material of the hinge region 520 is formed with a resilient memory that biases the wings 516 and 518 to a spread-apart condition (as FIG. 34 shows).
Each fastener 508 is carried within a grommet 510 on the flange area 506 (see FIG. 35). When the hinge region 520 is confined within the grommet 510 (as FIG. 35 shows), the wings 516 and 518 are retained against the resilient memory in an adjacent, closed condition. In response to the application of a pushing or punching force on the head 512 (see FIG. 35), the wings 516 and 518 are advanced in the closed condition out of the grommet 510, and into and through the adjacent vessel wall (see FIG. 36). Upon continued advancement, the hinge region 520 is freed from the confines of the grommet 510 (see FIG. 37). As a result, the wings 516 and 518 resiliently spring into their normal spread-apart condition.
In this arrangement, an intraluminal tool 522 (see FIG. 33) is deployed into the prosthesis 500 to exert a pushing or punching force upon the head 512 of a given fastener 508. In the illustrated embodiment, the tool 522 comprises a catheter 524 that carries a punch member 526 at its distal end. In a desired arrangement, the distal end of the catheter 524 is steerable, to aid in establishing point contact between the punch member 526 and the head 512 of the given fastener 508. The head 512 can include a recess 528 to receive and stabilize the tip of the punch member 526 with respect to the head 512 during use (see FIG. 34).
In use, the punch member 526 is manipulated to apply a pushing or punching force upon the selected fastener head 512. As FIGS. 35 and 36 show, the application of the pushing force by the punch member 526 forces the wings 516 and 518 against the near side of the vessel wall 34. The wings 516 and 518 are still in their closed condition, because the hinge region 520 is still confined within the grommet 510. The closed wings 516 and 518 form an obturator that penetrates tissue as it advances to the far side of the vessel wall. As the hinge region 510 is freed from the grommet 510 (FIG. 37), the wings 516 and 518 resiliently return to their spread-apart condition against the far side of the vessel wall. Upon removal of the punch member 526 (see FIG. 38), the head 512 and spread-apart wings 516 and 518 remain in their mutually opposed condition in the vessel wall, to secure the prosthesis 500 against the vessel wall. In use, the physician locates and manipulates the punch member 526 in succession against each fastener 508, to complete the anchorage of the prosthesis 500 to the vessel wall.
In one embodiment (see FIG. 39), each fastener 508 can include a tracking wire 530 that is releasably coupled to the head 512. The tracking wire 530 extends from the head 512 outside the body for access outside the vessel. In this arrangement, the punch member 526 includes a lumen to accommodate passage of the tracking wire 530. The tracking wire 530 guides the punch member 526 in an intraluminal path to the respective fastener 508. After the punch member 526 is manipulated to drive the fastener 508 into the vessel wall, the punch member 526 can be withdrawn over the tracking wire 530. The tracking wire 530 can be released from the now-secured head 512, e.g., by applying a moderate pulling force upon the tracking wire 530. The tracking wire 530 can then be withdrawn. The punch member 526 is sequentially guided over another tracking wire 530 for interaction with another one of the fasteners 508, until a desired degree of anchorage is achieved.
In an alternative embodiment, an integrated fastener assembly 502 on the prosthesis 500 can be used to temporarily tack the prosthesis 500 in place while a permanent anchoring technique is carried out. For example, in this arrangement, after using the integrated fastener assembly 502 to temporarily hold the prosthesis 500 in a desired location, the separate helical fasteners 28 are deployed in the manner previously described, to permanently anchor the prosthesis 500 against the vessel wall.
It will be appreciated that the components and/or features of the preferred embodiments described herein may be used together or separately, while the depicted methods and devices may be combined or modified in whole or in part. It is contemplated that the components of the directing device, fastener applier and helical fastener may be alternately oriented relative to each other, for example, offset, bi-axial, etc. Further, it will be understood that the various embodiments may be used in additional procedures not described herein, such as vascular trauma, arterial dissections, artificial heart valve attachment and attachment of other prosthetic device within the vascular system and generally within the body.
The preferred embodiments of the invention are described above in detail for the purpose of setting forth a complete disclosure and for the sake of explanation and clarity. Those skilled in the art will envision other modifications within the scope and sprit of the present disclosure.

## Claims

1. A system to implant a plurality of single tissue piercing fasteners one-at-a-time to desired fastening surfaces within a targeted endovascular region, the system comprising
a steerable directing device sized and configured to be deployed from a remote access site to a targeted endovascular region, the directing device including
a proximal end sized and configured to be disposed at the remote access site and a distal end sized and configured to be disposed at the targeted endovascular region,
a guide lumen extending between the proximal and distal ends,
a steering control assembly comprising at least one steering wire in the distal end and a control member on the proximal end coupled to the steering wire to serially deflect the distal end toward different desired fastening sites in the targeted endovascular region, and
a stabilization device sized and configured to be deployed when desired to maintain position of the steerable directing device while deflected with respect a desired fastening site,

a plurality of single tissue-piercing fasteners each comprising a body having a distal end for piercing and penetrating tissue in response to an implantation force, the body also having a proximal end,
a fastener attachment assembly separate from the directing device, the fastener attachment assembly including
a catheter body sized and configured to be serially introduced and retrieved by an operator through the guide lumen between the remote access site and the targeted endovascular region,
a drive cable carried at least partially within the catheter body, the drive cable including a distal end comprising a carrier being sized and configured, when the catheter body is retrieved from the targeted endovascular region, to be releasably coupled to the proximal end of a single fastener body, and
an actuator coupled to a proximal end of the drive cable that is operable to drive the carrier to generate the implantation force, the actuator including a sensing mechanism that normally disables operation of the actuator when the catheter body is retrieved from the targeted endovascular region and free of contact with a desired fastening site and that enables operation of the actuator only when the catheter body is introduced through the guide lumen in the targeted endovascular region and a desired degree of contact is sensed between the distal end of the fastener body on the carrier and the desired fastening site that is oriented by deflection of the distal end of the directing device and stabilized by the stabilization device within the targeted endovascular region.

2. A system according to claim 1
wherein the tissue-piercing fastener includes a stop structure associated with the proximal end to prevent over-penetration of the fastener body into tissue.

3. A system according to claim 1
wherein at least a portion of the drive cable is displaced within the catheter body in response to contact between the distal end of the fastener body on the carrier and the desired fastening surface oriented by deflection of the distal end of the directing device and stabilized by the stabilization device within the targeted endovascular region, and
wherein the sensing mechanism is coupled to the drive cable to sense displacement of the drive cable and to enable operation of the actuator when a predefined amount of displacement is sensed.

4. A system according to claim 3
wherein the sensing mechanism comprises a switch having a normally open condition disabling operation of the actuator and a closed condition enabling operation of the actuator, and
wherein the drive cable is coupled to the switch for moving the switch from the open condition toward the closed condition in response to the predefined amount of displacement.

5. A system according to claim 3
wherein the sensing mechanism includes an adjustment element for defining the defined amount of the displacement.

6. A system according to claim 1
wherein the sensing mechanism includes a rod that is displaced within the catheter body in response to contact between the distal end of the fastener body on the carrier and the desired fastening surface oriented by deflection of the distal end of the directing device and stabilized by the stabilization device within the targeted endovascular region, and
wherein the sensing mechanism is coupled to the rod to sense the displacement of the rod and to enable operation of the actuator when a predefined amount of displacement is sensed.

7. A system according to claim 1
wherein the desired fastening surface comprises tissue within the targeted endovascular region.

8. A system according to claim 1
wherein the desired fastening surface comprises a prosthesis located within the targeted endovascular region.