US20020032462A1 - Thermal securing anastomosis systems - Google Patents

Abstract

A sutureless anastomosis systems for securing a bypass graft to a host vessel or other tubular structure including a bypass graft and fitting. A compression mechanism may be used with the system for attachment of the bypass graft to the fitting. An electrode is connected to the fitting and an energy source. The energy source transmits energy to the electrode and causes the adjacent tissue to rise in temperature and bond to a vessel or fitting.

Description

• This application is related to the following applications: co-pending Provisional application Serial No. 60/111,948 filed Dec. 11, 1998; co-pending Provisional application Serial No. 60/088,705 filed Jun. 10, 1998; co-pending U.S. application Ser. No. 08/966,003 filed Nov. 7, 1997; co-pending Provisional application Serial No. 60/030,733 filed Nov. 8, 1996; and co-pending U.S. application Ser. No. 08/932,566 filed Sep. 19, 1997.[0001]
BACKGROUND OF THE INVENTION
• The invention relates to devices for deploying and securing the ends of bypass grafts and for providing a fluid flow passage between at least two vessel regions or other tubular structure regions. More particularly, the invention relates to bypass grafts that are thermally secured at target vessel locations thereby producing a fluid flow passage from the first vessel location through the bypass graft to the second vessel location. The bypass grafts and deployment systems of the invention do not require stopping or re-routing blood flow to perform an anastomoses between a bypass graft and a host vessel. Accordingly, this invention describes sutureless anastomosis systems that do not require cardiopulmonary bypass support when treating coronary artery disease.[0002]
• Stenosed blood vessels may cause ischemia and lead to tissue infarction. Conventional techniques to treat partially or completely occluded vessels include balloon angioplasty, stent deployment, atherectomy, and bypass grafting. Coronary artery bypass grafting (CABG) procedures to treat coronary artery disease have traditionally been performed through a thoracotomy with the patient placed on cardiopulmonary bypass support and using cardioplegia to induce cardiac arrest. Cardiac protection is required when performing bypass grafting procedures having prolonged ischemia times. Current bypass grafting procedures involve interrupting blood flow to suture or staple the bypass graft to the host vessel wall and create the anastomoses. When suturing or clipping the bypass graft to the host vessel wall, a generally large incision is made through the vessel and the bypass graft is sewn to the host vessel wall such that the endothelial layers of the bypass graft and vessel face each other. Bypass graft intima to host vessel intima apposition reduces the incidence of thrombosis associated with biological reactions that result from blood contacting the epithelial layer of a harvested bypass graft. This is especially relevant when using harvested vessels that have a small inner diameter (e.g. ≦2 mm).[0003]
• Less invasive attempts for positioning bypass grafts at target vessel locations have used small ports to access the anatomy. These approaches use endoscopic visualization and modified surgical instruments (e.g. clamps, scissors, scalpels, etc.) to position and suture the ends of the bypass graft at the host vessel locations. Attempts to eliminate the need for cardiopulmonary bypass support while performing CABG procedures have benefited from devices that stabilize the motion of the heart, retractors that temporarily occlude blood flow through the host vessel, and shunts that re-route the blood flow around the anastomosis site. Stabilizers and retractors still require significant time and complexity to expose the host vessel and suture the bypass graft to the host vessel wall. Shunts not only add to the complexity and length of the procedure, but they require a secondary procedure to close the insertion sites proximal and distal to the anastomosis site.[0004]
• Attempts to automate formation of sutureless anastomoses have culminated in mechanical stapling devices. Mechanical stapling devices have been proposed for creating end-end anastomoses between the open ends of transected vessels. Berggren, et al propose an automatic stapling device for use in microsurgery (U.S. Pat. Nos. 4,607,637; 4,624,257; 4,917,090; and 4,917,091). This stapling device has mating sections containing pins that are locked together after the vessel ends are fed through lumens in the sections and everted over the pins. This stapling device maintains intima to intima apposition for the severed vessel ends but has a large profile and requires impaling the everted vessel wall with the pins. Sakura describes a mechanical end-end stapling device designed to reattach severed vessels (U.S. Pat. No. 4,214,587). This device has a wire wound into a zig-zag pattern to permit radial motion and contains pins bonded to the wire that are used to penetrate tissue. One vessel end is everted over and secured to the pins of the end-end stapling device, and the other vessel end is advanced over the end-end stapling device and attached with the pins. Sauer, et al proposes another mechanical end-end device that inserts mating pieces into each open end of a severed vessel (U.S. Pat. No. 5,503,635). Once positioned, the mating pieces snap together thereby bonding the vessel ends. These end-end devices are amenable to reattaching severed vessels but are not suitable to producing end-end anastomoses between a bypass graft and an intact vessel, especially when exposure to the vessel is limited.[0005]
• Mechanical stapling devices have also been proposed for end-side anastomoses. These devices are designed to insert bypass grafts, attached to the mechanical devices, into the host vessel through a large incision and secure the bypass graft to the host vessel. Kaster describes vascular stapling apparatus for producing end-side anastomoses (U.S. Pat. Nos. 4,366,819; 4,368,736; and 5,234,447). Kaster's end-side apparatus is inserted through a large incision in the host vessel wall. The apparatus has an inner flange that is placed against the interior of the vessel wall, and a locking ring that is affixed to the fitting and contains spikes that penetrate into the vessel thereby securing the apparatus to the vessel wall. The bypass graft is itself secured to the apparatus in the everted or non-everted position through the use of spikes incorporated in the apparatus design.[0006]
• U.S. Surgical has developed automatic clip appliers that replace suture stitches with clips (U.S. Pat. Nos. 5,868,761; 5,868,759; and 5,779,718). These clipping devices have been demonstrated to reduce the time required when producing the anastomosis but still involve making a large incision through the host vessel wall. As a result, blood flow through the host vessel must be interrupted while creating the anastomoses.[0007]
• Gifford, et al provides end-side stapling devices (U.S. Pat. No. 5,695,504) that secure harvested vessels to host vessel walls maintaining intima to intima apposition. This stapling device is also inserted through a large incision in the host vessel wall and uses staples incorporated in the device to penetrate into tissue and secure the bypass graft to the host vessel.[0008]
• Walsh, et al propose a similar end-side stapling device (U.S. Pat. Nos. 4,657,019; 4,787,386; 4,917,087). This end-side device has a ring with tissue piercing pins. The bypass graft is everted over the ring; then, the pins penetrate the bypass graft thereby securing the bypass graft to the ring. The ring is inserted through a large incision created in the host vessel wall and the tissue piercing pins are used to puncture the host vessel wall. A clip is then used to prevent dislodgment of the ring relative to the host vessel.[0009]
• The end-side stapling devices previously described require insertion through a large incision, which dictates that blood flow through the host vessel must be interrupted during the process. Even though these and other clipping and stapling end-side anastomotic devices have been designed to decrease the time required to create the anastomosis, interruption of blood flow through the host vessel increases the morbidity and mortality of bypass grafting procedures, especially during beating heart CABG procedures. A recent experimental study of the U.S. Surgical One-Shot anastomotic clip applier observed abrupt ventricular fibrillation during four of fourteen internal thoracic artery to left anterior descending artery anastomoses in part due to coronary occlusion times exceeding 90 seconds (Heijmen, et al. A novel one-shot anastomotic stapler prototype for coronary bypass grafting on the beating heart: feasibility in the pig.[0010]J Thorac Cardiovasc Surg.117:117-25; 1999).
• All documents cited herein, including the foregoing, are incorporated herein by reference in their entireties for all purposes.[0011]
SUMMARY OR THE INVENTION
• The present inventions provide sutureless anastomosis systems that enable a physician to quickly and accurately secure a bypass graft to a host vessel or other tubular body structure. In addition, the invention enables the physician to ensure bypass graft stability, and prevent leaking at the vessel attachment points. The delivery systems of the invention do not require stopping or re-routing blood flow while producing the anastomosis as compared to some current techniques that require interrupting blood flow to suture, clip, or staple a bypass graft to the vessel wall.[0012]
• A need for bypass grafts and delivery systems that are capable of quickly producing an anastomosis between a bypass graft and a host vessel wall without having to stop or re-route blood flow. These anastomoses must withstand the pressure exerted by the pumping heart and ensure that blood does not leak from the anastomoses into the thoracic cavity, abdominal cavity, or other region exterior to the vessel wall.[0013]
• Current techniques for producing anastomoses during coronary artery bypass grafting procedures involve placing the patient on cardiopulmonary bypass support, arresting the heart, and interrupting blood flow to suture or staple a bypass graft to the coronary artery and aorta. Cardiopulmonary bypass support is associated with substantial morbidity and mortality. The embodiments of the invention are used to position and secure bypass grafts at host vessel locations without stopping or rerouting blood flow. Accordingly, the embodiments of the invention do not require cardiopulmonary bypass support and arresting the heart while producing anastomoses to the coronary arteries. In addition, the invention generally mitigates risks associated with suturing or clipping the bypass graft to the host vessel, namely bleeding at the attachment site and collapse of the vessel around the incision point.[0014]
• The invention addresses vascular bypass graft treatment regimens requiring end-to-end anastomoses and end-to-side anastomoses to attach bypass grafts to host vessels. The scope of the invention includes systems to position and thermally secure bypass grafts used to treat vascular diseases such as atherosclerosis, arteriosclerosis, fistulas, aneurysms, occlusions, and thromboses. In addition, the systems may be used to bypass stented vessel regions that have restenosed or thrombosed. The bypass grafts and delivery systems of the invention are also used to attach the ends of ligated vessels, replace vessels harvested for bypass grafting procedures (e.g. radial artery), and re-establish blood flow to branching vessels which would otherwise be occluded during surgical grafting procedures (e.g. the renal arteries during abdominal aortic aneurysm treatment). In addition, the invention addresses other applications including arterial to venous shunts for hemodialysis patients, bypassing lesions and scar tissue located in the fallopian tubes causing infertility, attaching the ureter to the kidneys during transplants, and bypassing gastrointestinal defects (e.g. occlusions, ulcers).[0015]
• One aspect of the invention provides fittings constructed from a metal (e.g. titanium), alloy (e.g. stainless steel or nickel titanium), thermoplastic, thermoset, composite of the aforementioned materials, or other suitable material, and designed to exert radial force at the vessel attachment points to maintain bypass graft patency. The fittings are advanced through the delivery system and are attached to the vessel wall at target locations. The delivery system is a combination of tear-away sheath, dilator, guidewire, and needle designed to be inserted into the vessel at the desired locations. The tubing, hub and valve of the tear-away sheath are configured to split so the entire sheath may be separated and removed from around the bypass graft after attaching the bypass graft to the host vessel. A plunger is used to insert the bypass graft and fitting combination through the sheath and into the vessel. The dilator and needle may incorporate advanced features, such as steering, sensing, and imaging, used to facilitate placing and locating the bypass graft and fitting combination.[0016]
• In accordance with the invention, the fittings incorporate mechanisms to thermally secure a bypass graft to a host vessel. One fitting configuration produces an anastomosis between a harvested bypass graft and a host vessel such that only the endothelial layer of the bypass graft is exposed to the interior of the host vessel. The invention also describes fittings designed to permit retrograde flow past the anastomosis site so as to maintain flow through the lesion and to branching vessels located proximal to the anastomosis site. A further aspect of the invention provides fittings having branches to accommodate multiple bypass grafts using a single proximal anastomosis.[0017]
• Fittings and accompanying components constructed from a conductive material may be used as electrodes to deliver radiofrequency energy to tissue contacting the electrode. Radiofrequency energy is applied to each fitting component (unipolar to an indifferent electrode, or bipolar between fitting components) to thermally secure the bypass graft to the vessel wall. Radiofrequency energy produces ohmic heating of adjacent tissue causing it to coagulate to the electrodes and locally shrinking the vessel wall around the fitting to produce an interference fit between the vessel wall and the bypass graft fitting. This not only thermally secures the bypass graft to the vessel wall but also prevents leaking around the bypass graft to host vessel interface.[0018]
• Still other objects and advantages of the present invention and methods of construction of the same will become readily apparent to those skilled in the art from the following detailed description, wherein only the preferred embodiments are shown and described, simply by way of illustration of the best mode contemplated of carrying out the invention. As will be realized, the invention is capable of other and different embodiments and methods of construction, and its several details are capable of modification in various obvious respects, all without departing from the invention. Accordingly, the drawing and description are to be regarded as illustrative in nature, and not as restrictive.[0019]
BRIEF DESCRIPTION OF DRAWINGS
• FIG. 1 shows a heart containing multiple bypass grafts positioned and secured to host vessels;[0020]
• FIGS. 2[0021]a-bare side-sectional views of a bypass graft support structure incorporating fittings;
• FIG. 2[0022]cshows a support structure, with an attached bypass graft, thermally secured to a host vessel at two locations;
• FIGS. 3[0023]a-cshow an end-to-end fitting that thermally secures a bypass graft to a host vessel;
• FIGS. 4[0024]a-ishow retaining rings used to bond the bypass graft to the fitting and/or the fitting to the vessel wall;
• FIGS. 5[0025]a-eshow retaining ring embodiments that act as electrodes for thermally securing the fitting to the host vessel wall;
• FIGS. 6[0026]a-dshow expandable retaining ring embodiments capable of serving as electrodes for thermally securing the fitting to the host vessel wall;
• FIGS. 6[0027]e-fshow an expandable retaining ring including petals to make an end-to-end fitting able to produce an end-to-side anastomosis;
• FIGS. 7[0028]a-bshow a bypass graft everted around and attached to end-to-end fittings, and secured to the host vessel;
• FIGS. 8[0029]a-dshow a bypass graft secured to the host vessel;
• FIGS. 9[0030]a-cshow a delivery system;
• FIG. 10 shows a delivery system;[0031]
• FIG. 11 shows a two-way plunger used to deliver the bypass graft and fitting combination through the sheath and into the host vessel;[0032]
• FIGS. 12[0033]a-cshow an alternative plunger embodiment;
• FIG. 13 shows a bypass graft and fitting combination being inserted through a sheath;[0034]
• FIG. 14 shows a schematic of the system used to thermally secure a bypass graft to a host vessel wall;[0035]
• FIGS. 15[0036]a-eshow an end-to-side fitting that may be delivered past a vessel wall without the need for a sheath;
• FIGS. 16[0037]a-gshow alternative end-to-side fitting embodiments that may be delivered past a host vessel wall without the need for a sheath;
• FIGS. 17[0038]a-bshow an end-to-side fitting incorporating a retaining ring with petals;
• FIGS. 18[0039]a-gshow an end-to-side fitting for host vessels having small and medium diameters;
• FIGS. 19[0040]a-fshow a foldable end-to-side fitting;
• FIGS. 20[0041]a-bshow an end-to-side fitting incorporating an electrode structure in the petals;
• FIGS. 21[0042]a-dshow an end-to-side fittings having an electrode incorporated in the fitting;
• FIGS. 22[0043]a-bshow an end-to-side fitting containing an electrode and able to fold into a low profile;
• FIG. 23 shows a bypass graft and fitting combination attached to a host vessel and designed to preserve flow proximal to the anastomosis site;[0044]
• FIGS. 24[0045]a-bare close-up views of the bypass graft and fitting combination shown in FIG. 23;
• FIGS. 24[0046]c-hshow alternative bypass graft and fittings designed to maintain retrograde blood flow;
• FIG. 25 is a schematic of the system used to thermally secure the ends of the bypass graft to the vessel wall;[0047]
• FIGS. 26[0048]a-bshow an end-to-end bypass graft having an electrode incorporated in the bypass graft;
• FIGS. 27[0049]a-bshow an end-to-end bypass graft having an expandable and compressible electrode secured to the bypass graft;
• FIGS. 28[0050]a-bshow tear-away sheath embodiments;
• FIGS.[0051]29 shows a fitting system;
• FIGS. 30[0052]a-dshow other embodiments of a fitting system;
• FIGS. 31[0053]a-dshow other embodiments of a fitting system; and
• FIGS. 32[0054]a-bshow other embodiments of a fitting system.
DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS
• The fittings and delivery systems are intended to produce anastomoses between bypass grafts and host vessels to treat vascular abnormalities such as stenoses, thromboses, other occlusions, aneurysms, fistulas, or other indications requiring a bypass graft. The systems are useful in bypassing stented vessels that have restenosed. Some approaches to treating stenosed stents have not been successful and reliable at removing the lesion and opening the vessel lumen. The approach described by this invention, produces a blood flow conduit around the stented lesion and mitigates concerns associated with damaging the stent or forming emboli when removing deposits attached to the stent. The fittings are used for securing and supporting the ends of transected vessels cut during organ transplantations. The embodiments also provide mechanisms to secure branching vessels to a replacement graft during surgical procedures in which the branching vessels would otherwise be occluded from the blood flow (e.g. reattaching the renal arteries, mesenteric artery, celiac artery, and intercostal arteries during treatment of abdominal aortic aneurysms that are pararenal, suprarenal, or thoracoabdominal in classification).[0055]
• Referring more particularly to the drawings, FIG. 1 illustrates bypass grafts secured to host vessels during coronary artery bypass grafting (CABG) procedures.[0056]Bypass graft16 provides a blood flow passage from the aorta to the right coronary artery. An end-to-side fitting18 is used to secure the proximal end of thebypass graft16 to the aorta and fitting18 or end-to-end fitting20 is used to secure the distal end of the bypass graft to the right coronary artery.Bypass graft16 provides a blood flow passage along a small vessel such as a coronary artery by securing the bypass graft to the host vessel withfittings18,20.Bypass graft16 is secured to the aorta with a fitting18,20 that branches into distinct bypass grafts which are further secured to the left anterior descending artery and circumflexartery using fittings18,20. The bypass grafts and fittings in these examples demonstrate representative applications and should not limit the scope of use for the embodiments of the invention. It should be noted that the combination of fittings used to secure abypass16 graft to a host vessel, along a host vessel, or between host vessels depends on the application.
• The[0057]bypass graft16 may be a synthetic graft material biological bypass graft, harvested vessel, or other tubular body structure, depending on the indication. The harvested vessels may be an internal mammary artery, radial artery, saphenous vein or other body tubing. Harvested vessels may be dissected using newer minimally invasive, catheter-based techniques or standard surgical approaches. Fittings in accordance with the invention are designed to attach bypass grafts to host vessels (or other tubular structures). Thefittings18,20 used to position and attachsuch bypass grafts16 are extensions of the collet and grommet embodiments described in U.S. application Ser. No. 08/966,003 filed Nov. 7, 1997. An advantage of biological bypass grafts over available synthetic materials is the reduction in thrombosis, especially when using small diameter (e.g. ≦2 mm) bypass grafts. The fittings and delivery systems of the invention are generally equally effective at positioning and securing all types of bypass grafts, biological and synthetic.
• Synthetic bypass grafts may be manufactured by extruding, injection molding, weaving, braiding, or dipping polymers such as PTFE, expanded PTFE, urethane, polyamide, nylon, silicone, polyethylene, collagen, polyester or composites of these representative materials. These materials may be fabricated into a sheet or tubing using one or a combination of the stated manufacturing processes. The sides of sheet materials may be bonded using radiofrequency energy, laser welding, ultrasonic welding, thermal bonding, sewing, adhesives, or a combination of these processes to form tubing. The synthetic bypass graft may also be coated, deposited, or impregnated with materials, such as paralyne, heparin, hydrophilic solutions, or other substrates designed to reduce thrombosis or mitigate other risks that potentially decrease the patency of synthetic bypass grafts. The primary advantage of synthetic bypass graft materials is the ability to bond the bypass graft to the fittings prior to starting the procedure or incorporate the fittings into the bypass graft design by injection molding or other manufacturing process. Currently, synthetic bypass grafts are indicated for blood vessels having medium and large diameters (e.g. >3 mm), such as peripheral vessels, tubular structures such as the fallopian tubes, or shunts for hemodialysis. However, medical device manufacturers such as Possis Medical, Inc. and Thoratec Laboratories, Inc. are clinically evaluating synthetic bypass grafts for coronary indications.[0058]
• Support members may be incorporated into a graft as referenced in co-pending U.S. application Ser. No. 08/932,566 filed Sep. 19, 1997 and in co-pending U.S. application Ser. No. 08/966,003 filed Nov. 7, 1997. When using synthetic bypass grafts, the support members may be laminated between layers of graft material. The[0059]synthetic bypass graft16 may be fabricated by extruding, injection molding, or dipping a primary layer of the graft over a removable mandrel; positioning, winding or braiding the support members on the primary layer; and extruding, injection molding, or dipping a secondary layer over the material/support member combination. The support members preferably have a shape memory. Memory elastic alloys, such as nickel titanium, exhibiting stress-induced martensite characteristics may be used to reinforce the bypass graft and/or vessel wall and prevent permanent deformation upon exposure to external forces.
• Alternatively,[0060]synthetic bypass grafts16 incorporating support members may be fabricated using cellulosic materials such as regenerated cellulose. Cellulosic materials may be extruded, wrapped, injection molded, or dipped in layers to laminate the support members between graft material layers. Cellulosics, and other such materials, which have a high water adsorption rate, are relatively stiff when dehydrated and flexible when hydrated. This characteristic provides a means to maintain a self-expanding material such as the support members in a collapsed state. The cellulosic material in its dry, stiff state counteracts the radial force of the self-expanding support members and prevents the graft from expanding until it becomes hydrated, thus more flexible. When thebypass graft16 is inserted through the delivery system and into the vessel, the cellulosic material contacts fluid, causing it to become more flexible and the support members of thebypass graft16 to expand towards its resting state and the graft into intimate contact with the vessel wall.
• [0061]Biological bypass grafts16 may be reinforced with asupport structure30 as shown in FIGS. 2a-c.Thissupport structure30 may consist of a wire material wound into a helix or braided into a mesh. Other reinforcing structures that limit expansion of thebypass graft16 may also be used. Thesupport structure30 is bonded to fittings at each end by spot welding, crimping, soldering, ultrasonic welding, thermal bonding, adhesively bonding, or other bonding process, depending on the materials. Thesupport structure30 defines a lumen into which thebypass graft16 is inserted. After advancing thebypass graft16 through thesupport structure30, thebypass graft16 is secured to the fittings at each end of thesupport structure30. Thesupport structure30 generally reduces the potential for kinking of thebypass graft16, limits the radial expansion of thebypass graft16, prevents aneurysm formation, and increases the burst strength of thebypass graft16. By mitigating the failure mechanisms ofbypass grafts16 such as the saphenous veins, such reinforcing structures may improve the long-term durability and patency of thebypass graft16.
• The[0062]support structure30 may alternatively be a synthetic graft material formed into a tube, with or without support members. Thesupport structure30 may be fabricated from a polymer that is macroporous to permit blood leaking through the bypass graft to flow outside the support structure. Biological bypass grafts typically have branches that are sutured or stapled closed while harvesting the vessel and may leak for a period of time immediately after implantation. Blood leaking through a biological bypass graft enclosed in a nonporous or microporous (e.g. pore size <8 μm) support structure may accumulate between the bypass graft and thesupport structure32 and occlude the bypass graft depending on the pressure gradient between the inside of thebypass graft16 and the space between the graft and thesupport structure30. For applications where the biological bypass graft is completely impervious to leaking or where the external surface of the biological bypass graft can be bonded to the support structure (e.g. using adhesives), nonporous or microporous support structures may be used.
• The[0063]support structure30 is preferably affixed to the fittings before attaching thebypass graft16 to the fittings. This ensures the support structure reinforces the entire length of thebypass graft16. Using a support structure that is not affixed to the fittings may cause kinking of the bypass graft in the region between the anastomosis site and the end of the support structure, which defines a region where the bypass graft is not reinforced. Thesupport structure30 incorporates fittings at each end for attachment of a harvestedvessel16 and for securing the bypass graft to thehost vessel38. As shown in FIGS. 2a-b,a graspingtool50 including a suture with a noose or a wire with a distal gripping end such as forceps, is fed through the support structure and is used to grab the harvestedvessel16. The harvestedvessel16 is pulled through thesupport structure30 such that a length of the harvested vessel extends beyond both ends of the support structure fittings. FIG. 2cshows the ends of the harvestedvessel16 everted around the support structure fittings and secured at the notchedregions40 of the fittings using retaining rings42.Electrodes44 may be included in the support structure to thermally secure thesupport structure30 and the bypass graft to thehost vessel wall39. The blood flowing through thebypass graft16 contacts the endothelial layers of the harvested bypass graft and host vessel thereby minimizing the potential for thrombosis or biological reactions to foreign materials.
• When microporous or nonporous support structures may be used, the support structures may serve dual purposes. They may function as synthetic bypass grafts designed to produce two end-end anastomoses at opposite ends of the bypass grafts. The support structure/bypass grafts may be configured with one or both ends incorporating fittings that enable end-side anastomoses. They also function as sutureless anastomosis devices to attach harvested vessels and reinforce the biological bypass grafts. This combined functionality minimizes the product portfolio required for bypass grafting indications because a single device may reinforce and facilitate attaching harvested vessels between anastomosis sites and act as a synthetic bypass graft capable of producing sutureless anastomoses.[0064]
• The bypass graft fittings are constructed from a metal (e.g. titanium), alloy (e.g. stainless steel or nickel titanium), thermoplastic, thermoset plastic, silicone or combination of the aforementioned materials into a composite structure; other materials may also be used. The fittings may be coated with materials such as paralyne or other hydrophilic substrates that are biologically inert and reduce the surface friction. Alternatively, the fittings may be coated with heparin or thrombolytic substances designed to prevent thrombosis around the attachment point between the bypass graft and the host vessel. The fittings consist of one or more components designed to secure a bypass graft to the fitting and the fitting to the host vessel wall for a fluid tight bond between the bypass graft and the host vessel. The fittings may be used at end-to-end anastomoses for applications where retrograde blood flow is not essential (e.g. total occlusions) as shown in FIGS. 2[0065]cand8a;end-to-side anastomoses for medium and small diameter vessels (e.g. peripheral vessels and coronary vessels) where retrograde blood flow is essential as shown in FIG. 19c;and end-to-side anastomoses for large diameter vessels (e.g. the aorta) as shown in FIG. 18a.The end-side fittings may be configured to orient the bypass graft at an angle, A, relative to the host vessel ranging between approximately 30 and 90 degrees. This helps optimize fluid flow through the bypass graft.
• FIGS. 3[0066]a-cshow an end-end fitting20 designed to secure bypass grafts constructed from an internal mammary artery, radial artery, saphenous vein, or other harvested vessel such that only the endothelial layer of the bypass graft is exposed to blood flow. In FIGS. 3a-c,thebypass graft16 is fed through the interior of the fitting and is wrapped around the distal end. A grasping tool may be used to pull the bypass graft through the fitting, especially when using long fittings. An everting tool may be used to wrap the bypass graft around the fitting prior to securing the bypass graft to the fitting. After the bypass graft is everted around the fitting, a retainingring62 is positioned over the everted bypass graft to compress it against the fitting. This secures the bypass graft to the fitting. The retainingring62 is connected to asignal wire64 that is routed to a radiofrequency generator to deliver radiofrequency energy to the retainingring62 for thermal securing of the fitting to thehost vessel38.
• FIGS. 4[0067]a-ishow embodiments of the retainingring62 used to secure thebypass graft16 to the fitting. The retaining rings may be fabricated from a metal, alloy, thermoplastic material, thermoset, composite of these materials, or other material. However, the retaining rings must permit at least 30% enlargement in diameter without becoming permanently deformed. Thus, after placement, the retaining ring will compress around the bypass graft and fitting interface to form a secure seal. In FIGS. 4a-f,the retaining ring is a preshaped member having a rectangular, circular, or elliptical cross-section and eyelets63 that facilitate positioning the retaining ring over the fitting and may be used to suture the retaining ring closed for additional support. The retaining ring shown in FIGS. 4a-bhas a preshaped member wound beyond a single turn. When theeyelets63 are squeezed together, the diameter of the retaining ring enlarges making it easier to position over the bypass graft and fitting combination. In FIGS. 4c-d,the retainingring62 is a coiled wire extending to just less than a single turn. When theeyelets63 are spread apart, the diameter of the retaining ring enlarges.
• The retaining[0068]ring62 shown in FIG. 4gis a preshaped member wound beyond a single turn and having radiused edges and ends. One representative fabrication process for the preshaped retaining ring involves forming the raw material into a desired geometry and exposing the material to sufficient heat to anneal the material into this predetermined shape. This process applies to metals (e.g. nickel titanium) and polymers. The preshaped retaining ring configuration is expanded by inserting the expansion tool into the middle of the retaining ring and opening the expansion tool thereby enlarging the diameter of the retaining ring. Once the retaining ring is positioned, the force causing the retaining ring to enlarge is removed causing the retaining ring to return towards its pre-formed shape thereby compressing the bypass graft over the fitting. This retaining ring may also be used to secure a fitting to a host vessel since this retaining ring may be expanded to expose an opening between opposite ends adapted for placement over the host vessel. Once positioned over the host vessel to fitting interface, the retaining ring is allowed to return towards its preformed shape thereby compressing the host vessel against the fitting.
• The retaining rings may incorporate elastic memory characteristics. For example, a retaining ring shown in FIG. 4[0069]g,may be manufactured from a deformable material and crimped over the bypass graft to fitting interface or host vessel wall to fitting interface for securing purposes. FIG. 4hshows another retaining ring that does not incorporate elastic memory characteristics. This retaining ring is opened for positioning around the bypass graft to fitting interface or the host vessel to fitting interface and is closed thereby causing the teeth to engage and lock the retaining ring in the closed position. Further closing the retaining ring causes the diameter to decrease and increase compression. FIG. 4ishows another retainingring62 configuration having a preshaped member wound beyond a single turn. This embodiment also permits expansion of the retaining ring to facilitate positioning, but is configured to form a complete ring in its resting shape.
• FIGS. 5[0070]a-eand FIGS. 6a-fshow retaining rings62 which are particularly useful when utilizing the thermal securing process in attaching a bypass graft and fitting to a host vessel. The retaining rings62 may be embedded in the bypass graft when using synthetic materials or advanced over the bypass graft and fitting interface to produce an interference fit at the bond joint. The retaining rings62 shown in FIGS. 6a-dmay be enlarged while being deployed around the bypass graft and fitting combination and allowed to return to its preformed shape, once positioned, thereby securing the bypass graft to the fitting and providing a fluid tight seal. The retaining rings62 havenumerous edges65 including straight notches as shown in FIG. 5b,slanted notches as shown in FIG. 5d,holes through the retaining ring, spaces defined by mesh material, or other geometry forming edges. Theedges65 produce high current densities when radiofrequency energy is transmitted through the retaining rings. The retaining ring electrodes have several spaces into which the vessel can shrink and coagulum can infiltrate thereby providing adherence between the host vessel and the retainingring62. The retaining rings62, shown in FIGS. 6e-f,incorporatepetals67 so that an end-to-end fitting may be used for an end-to-side anastomosis.
• The bypass graft may be bonded to the fittings prior to securing the fittings to the host vessel. This step may be performed outside the patient to allow the physician to ensure a strong and leak resistant bond. Another advantage of the fittings is that they only expose the endothelial layer of a biological bypass graft to blood flow which generally prevents thrombosis and other interactions between foreign materials and blood.[0071]
• Conventional anastomosis techniques require a relatively large incision through the vessel wall and use of sutures, commercially available clips, or stapling devices to bond the end of the bypass graft to the exposed edges of the vessel wall. In certain cases, the structural integrity of the vessel wall may be weakened causing the vessel to collapse at the anastomosis site, especially when the bypass graft is not appropriately aligned to the host vessel incision. Therefore, the delivery system embodiments are designed to access the vessel through a small puncture in the vessel wall. The delivery systems are designed to prevent excess blood loss when accessing the host vessel and deploying the bypass graft and fitting combination thereby eliminating the need to stop or re-route blood flowing through the host vessel. This approach also generally improves the leak resistance around the fitting due to elastic compression of the vessel wall around the fitting and aligns the bypass graft to the host vessel wall at the anastomosis site.[0072]
• The particular delivery system embodiment used depends on the application. For catheter-based bypass grafting applications, further referenced in U.S. application Ser. No. 08/966,003 filed Nov. 7, 1997, a catheter (e.g. guiding member) is intralumenally advanced to the proximal anastomosis site. A puncture device (e.g. needle) is used to perforate the vessel wall and enable advancing a guiding member exterior to the vessel. A dilating member expands the opening to atraumatically advance the guiding member through the vessel wall. A balloon may be attached to the guiding member and inflated to restrain the guiding member outside the host vessel and to prevent leaking at the puncture site. The balloon is deflated while the guiding member is advanced through the vessel wall. The catheter is then manipulated to the distal anastomosis site. The puncture device is used to perforate the vessel wall and access the interior of the vessel at the distal anastomosis site. A guidewire may be advanced through the puncture device or the puncture device may function as a guidewire to provide a passage to advance the guiding member into the interior of the host vessel at the distal anastomosis site. Once the guiding member is advanced through the puncture and into the interior of the host vessel, the bypass graft is advanced inside or outside the guiding member to the distal anastomosis site. A stylet may be used to advance the bypass graft along the guiding member or maintain the position of the bypass graft as the guiding member is retracted. The balloon attached to the guiding member may again be inflated to keep the guiding catheter within the vessel at the distal anastomosis site and prevent leaking. The bypass graft is secured to the host vessel at the distal anastomosis site. The guiding member may be retracted so the bypass graft is able to contact the host vessel wall at the proximal anastomosis site. If a balloon was inflated to maintain the position of the guiding member within the vessel, it must be deflated prior to retracting the guiding member through the vessel wall. The bypass graft is then secured to the host vessel wall at the proximal anastomosis site and the guiding member is removed leaving the bypass graft as a conduit for blood to flow from the proximal anastomosis to the distal anastomosis. The fittings used to secure the bypass graft to the host vessel wall at the proximal and distal anastomosis sites depend on the application and whether retrograde blood flow through the anastomosis site is desired. Some fittings used for end-to-end anastomoses may not permit retrograde blood flow.[0073]
• FIGS. 7[0074]a-bshow fittings60 attached in-line along avessel38. Thefittings60 are designed to support the bypass graft at the vesselwall insertion site90 and prevent thehost vessel38 from constricting the diameter of thebypass graft16. Thebypass graft16 is advanced through the fitting60 and is everted around the distal end of the fitting60. A retainingring42 is used to secure thebypass graft16 to the fitting60 and is positioned within the notchedregion40.
• The bypass graft may be secured to the vessel by transmitting radiofrequency energy to[0075]electrodes44 attached to thebypass graft16. Theelectrodes44 may be conductive fittings or retaining rings bonded to the bypass graft as previously described. Theelectrodes44 may be fabricated from stainless steel, nickel titanium, platinum, platinum iridium, gold, titanium, tungsten, tantalum, or other material and may provide structural support to the bypass graft.Electrodes44 may be incorporated into the fittings to thermally secure the fitting and the bypass graft to the vessel wall at each anastomosis. The retaining rings may serve to bond the bypass graft to the fitting and act as the electrodes for thermal securing. Alternatively, the electrodes may be added to the fitting as separate components aside from the retaining rings. When fittings are laminated within layers of synthetic bypass graft material eliminating the need for retaining rings, the electrodes will be bonded to the fittings or bypass graft during manufacturing. These end-to-end fittings are particularly useful when performing in-line anastomoses along a vessel and around a vascular abnormality. They are also useful to treat total occlusions when retrograde blood flow is not beneficial.
• For surgical applications, physicians may access the anastomosis sites from the exterior surface of the host vessel. Unlike the catheter-based approach where the bypass graft is advanced past the distal end of the delivery catheter during deployment, the delivery system of the surgical approach must permit removal after both ends of the bypass graft have been secured and the delivery system resides around the attached bypass graft.[0076]
• FIGS. 8[0077]a-dshow that thebypass graft16 does not need to be everted. For example, synthetic bypass grafts may be attached to the exterior of the fitting65. The fitting65 may be laminated between layers of thebypass graft16.
• FIGS. 9[0078]a-cshow steps to position a bypass graft and fitting combination through avessel wall39. Aneedle100 is inserted through adilator102 and asheath104. The needle, dilator, and sheath combination is positioned at the target vessel location. Especially for minimal access procedures involving endoscopic visualization and manipulation through small incisions, sensors may be incorporated in the needle, dilator, and/or sheath to position the delivery system at the target location. The sensors can include ultrasonic transducers, such as those fabricated from piezoelectric material, doppler crystals, infrared transducers, or fiberoptics. Alternatively a lumen may permit the injection of radiopaque contrast material within the vessel to verify the position using fluoroscopy.
• FIG. 9[0079]aillustratesneedle100 being used to puncture thevessel wall39 and advancing into the interior of thevessel38. Theneedle100 may be designed with a tapered or stepped distal end to restrict movement of the needle beyond the end of thedilator102 and prevent perforating the opposite side of the vessel or unwanted anatomy. A guidewire (not shown) may be advanced through the needle to provide a path over which the dilator and sheath may be advanced. When using a guidewire, the needle may be retracted to prevent unwanted perforations or abrasions to the vessel or adjacent anatomy. Thedilator102 is then advanced over theneedle100 or guidewire into the host vessel. Subsequently, the needle100 (if not already retracted to insert the guidewire) may be removed from the vessel or retracted inside thedilator102. Thedilator102 is tapered to provide a smooth transition when advancing through thevessel wall39. Thevessel wall39 forms a seal around thedilator102 to preventing excess blood leakage from the vessel. Asheath104 having a radius or tapered distal end forms a smooth transition around thedilator102. Once thedilator102 is positioned within thevessel38, thesheath104 may be advanced over thedilator102 and into thevessel38 as shown in FIG. 9b.At this point, thedilator102 may be removed. Insertion of asheath104 into avessel38 over adilator102 andneedle100 is commonly used by physicians when performing the Seldinger technique during catheterization procedures or inserting I.V. catheters into veins for withdrawal of blood or introduction of medicines. Thesheath104 anddilator102 may be constructed from polyethylene, or other polymer and be extruded or molded into a tube. Thesheath104 anddilator102 may incorporate a braided layer laminated between two polymers to resist kinking and improve the column strength and torque response. A taper and radius may be formed in the distal end of the dilator and sheath by thermally forming the raw tubing into the desired shape.
• The[0080]hub106,108 on thesheath104 anddilator102, respectively may be fabricated from polycarbonate, polyethylene, PEEK, urethane or other material and be injection molded, adhesively bonded, or thermally bonded to the tube. Thehub106 contains at least one and preferably two grooves, slits, or series of perforations along the hub to enable the operator to split the hub when removing the sheath from around the bypass graft. Thehub106 houses ahemostatic valve110 constructed of silicone or other material having a large percent elongation characteristic. Thehemostatic valve110 prevents excess blood loss through the sheath when positioned into the vessel. Thevalve110 also incorporates at least one groove, slit, or series of perforations to permit separation when tearing the sheath from around the bypass graft. A side port may be included to aspirate and flush the sheath. The hub may alternatively be a separate piece from the tear-away sheath and be independently removed from around the bypass graft. This hub may include a luer fitting to enable screwing onto a mating piece of the tear-away sheath, or other mechanism to permit removable attachment of the hub to the tear-away sheath. This hub may incorporate at least one groove, slit, or series of perforations to enable splitting the hub to form an opening to remove the hub from around the bypass graft. Alternatively, the hub may include a slot which may be closed to prevent fluid leaking and may be aligned to form an opening for removal from around the bypass graft.
• The[0081]needle100 anddilator102 may incorporate a number of additional features to facilitate positioning at the host vessel. For example, a number of sensors may be placed within the tapered region of the dilator such that they face axially or laterally with respect to the axis of the dilator lumen. As a result, imaging modalities may be directed forward or around the periphery of the dilator. For both configurations, the sensors may be oriented around thedilator102 at known angular increments. Sensors used to position the delivery system include ultrasonic transducers, such as those fabricated from piezoelectric material, infrared transducers, or fiberoptics. For example, four ultrasonic transducers may be placed around thedilator102 separated by 90 degrees to provide a 3-dimensional interpretation of anatomic structures in front of the dilator to better detect the host vessel. Conventional phased array imaging modalities may be used to derive images extending distal to thedilator102 or around the circumference of thedilator102. Sensors may be placed at the distal end of theneedle100 to facilitate positioning the needle at vessel location. The sensors may be used with the dilator sensors to provide better imaging resolution and determine the location of the needle tip relative to the end of thedilator102.
• Another feature which may be used in the[0082]dilator102 andneedle100 is the inclusion of unidirectional or bidirectional steering. A steering mechanism may be positioned within the sheath, dilator, and/or needle. Typically, the steering mechanism may include a pull-wire terminating at a flat spring or collar in the sheath, dilator, or needle. The steering system has a more flexible distal section compared to the proximal tube body. When tension is placed on the pullwire, the sheath, dilator, or needle is deflected into a curve which helps direct the delivery system to the target vessel location. The pullwire may be wound, crimped, spot welded or soldered to the flat spring or collar placed in the sheath or dilator. This provides a stable point within the sheath or dilators for the pullwire to exert tensile force thus steer the sheath or dilator. To incorporate steering in the needle, the pullwire may be spot welded or soldered to one side of the needle hypotubing. The proximal tube body of the sheath or dilator may be reinforced by incorporating a helically wound wire within the tube extrusion to provide column support from which to better deflect the distal section.
• FIG. 10 shows[0083]sheath118 with at least onegroove120, slit, or series of perforations formed along the tube andhub122 to provide a tear-away mechanism along at least one side for use after securing the bypass graft to the vessel wall. Alternatively, thesheath118 may include a section of tubing material pre-split into at least two sections such that the tubing tends to continue to split into two pieces as the sections are pulled apart. This feature is essential for removal of thesheath118 from around abypass graft16 when thesheath118 is unable to slide past the opposite end of thebypass graft16. Support material incorporated into a tear-away sheath to improve column strength should split along the grooves formed in the sheath. The support material may be fabricated into two braided sections oriented on opposite sides of the sheath such that the grooves reside along the spaces between the braided sections. Alternatively, the supporting material may be strands of wire (e.g. stainless steel, nylon, etc.) laminated between layers of sheath material and oriented axially along the longitudinal axis of the sheath. The tear-awaysheath118 may further incorporate features to maintain blood flow through the host vessel while positioned inside the lumen of the host vessel as further referenced in FIGS. 28a-b.
• The[0084]plunger124 is designed to insert thebypass graft16 and fitting130 as an attached unit and includes a lumen to pass thebypass graft16 through while inserting the fitting130 into the host vessel. Aplunger124 is essential when inserting biological bypass grafts or synthetic bypass grafts that do not have adequate column strength to be pushed through the hemostatic valve of the sheath. In addition, theplunger124 protects the bypass graft during insertion through the hemostatic valve of the sheath. After one side of the bypass graft is placed at a first vessel location, theplunger124 must be removed. Theplunger124 may be retracted beyond the opposite end of the bypass graft, if possible, or theplunger124 may be split along at least onegroove120,126 incorporated along the side of the plunger. Theplunger124 is used to insert the opposite end of the bypass graft, attached to a fitting, through a second sheath inserted at a second vessel location. After attaching the second end of the bypass graft to the vessel, theplunger124 is contained between the ends of the attached bypass graft and must be removed by tearing the plunger along at least one and preferably twogrooves120,126. The tear-awaygroove120,126 must permit splitting the plunger wall andhub128 along at least one side to remove theplunger124 from around the bypass graft. To facilitate removal from around the bypass graft, theplunger124 and tear-awaysheath118 discussed above preferably incorporate grooves, slits, orperforations126 on two sides to enable separation into two components.
• FIG. 11 shows a bypass graft[0085]assembly containing fittings60 already attached at thebypass graft16 ends andplunger140 preloaded onto thebypass graft16. Thisplunger140 is designed with thehub142 located at the middle region to facilitate insertion of both ends of the bypass graft and attached fittings without removal and repositioning of the plunger prior to insertion of the second end of the bypass graft. Theplunger140 has grooves, slits, orperforations126 along at least one side of theplunger tube144 andhub142 to permit removal after positioning and attachment of the bypass graft at both ends.
• FIGS. 12[0086]a-cillustrate another plunger embodiment.Plunger150 includes an axial slot through its entire length. The slot enables pulling of theplunger150 from the side of the bypass graft when removing the plunger and permits pressing of theplunger150 over the side of the bypass graft when placing the plunger over the bypass graft. Oneend152 has a short length stepped down to form a smaller outer diameter that fits inside the inner diameter of the fitting and provides a stable anchor to insert and manipulate during delivery of the bypass graft and fitting combination into the vessel. Theother end154 has the inner diameter reamed out and notched for a short length to fit over the outer diameter of the bypass graft and fitting combination during manipulations. Theplunger150 maintains its integrity upon removal from the bypass graft and may be used to deploy multiple bypass graft and fitting combinations through sheaths.
• FIG. 13 is an enlarged view of[0087]sheath172 inserted intohost vessel39 with dilator removed, and withbypass graft16 everted about fitting170 and retained by ring174.
• For situations where blood flow is occluded and an incision has been made through the vessel wall, a modified hockey stick introducer may be used to insert the bypass graft and fitting combination into the host vessel. The hockey stick introducer has a tapered distal end and a partially enclosed body. This introducer is advanced through the incision and is used to expand the vessel wall so the bypass graft and fitting combination may be advanced through the lumen of the introducer and into the host vessel without catching the top part of the fitting on the vessel wall. This is especially important when the bypass graft and fitting combination has an outer diameter larger than the inner diameter of the vessel where the host vessel must be expanded to insert the bypass graft and fitting combination. The introducer may incorporate an extension perpendicular to the longitudinal axis that provides a handle to manipulate the introducer.[0088]
• FIG. 14[0089]shows electrodes181 including conductive material bonded to the bypass graft or fitting180. Theelectrodes181 are used to transmit energy to the vessel wall and may be deposited (e.g. ion beam assisted deposition, sputter coating, pad printing, silk screening, soldering, or painting conductive epoxy) on thefittings180,bypass graft16 or retaining ring182. Theelectrodes181 may be flexible and follow the contours of the fittings and/or bypass graft. The electrodes may be formed in a helix, mesh, or braid and bonded to the exterior surface of the fitting and/or bypass graft.Signal wires183 and184 are connected to the electrodes through spot welding, mechanical fit, or soldering, and are routed to the leads of aradiofrequency generator186. A large surface area indifferent ground pad may be placed on the patient's back, thigh, or other location so radiofrequency energy may be delivered in a unipolar configuration. Alternatively, energy may be delivered between electrode pairs in bipolar configuration.
• By delivering radiofrequency energy to the electrodes, tissue contacting the electrodes heats and coagulates the vessel wall to the electrode and provides a secure, leak resistant bond. A dramatic increase in impedance results from the formation of coagulum on the electrode. This measurement of the bond strength can be used to determine the quality of the bond generated between the[0090]electrode44 and thevessel wall39. Different impedance thresholds may specify different degrees of thermal bonding. Initial thermal bonding has been demonstrated during experimental studies when impedance increased above 300Ω using a signal frequency of 500 kHz, which represented a threshold approximately 50% above baseline. The baseline impedance differs depending on the frequency of the signal and the surface area of the electrode; these characteristics must be taken into account when determining the thresholds. Commercial electrosurgical generators operating at a frequency of approximately 500 kHz commonly measure impedances up to and exceeding lkQ when producing complete hemostasis using tissue coagulating probes.
• FIGS. 15[0091]a-eshow a system for producing an end-to-side anastomosis that compresses the vessel wall between two fitting components. In this embodiment, the fitting196 incorporates a flareddistal region190 having aslot192 that defines two edges. The slotted distal end of the fitting is inserted through apuncture194 of thevessel wall39 by positioning the edge of the slotted fitting at thepuncture site194, angling the distal flaredregion190 so the edge may be further advanced through the vessel wall, and rotating the fitting196. Upon further rotation of the fitting196, the entire flared region of the fitting is advanced into the interior of thevessel38, as shown in FIG. 15d.Then acompression ring198 is positioned over the fitting196 and past thetabs200 to compress thevessel wall39 between the flareddistal end190 and thecompression ring198.
• FIGS. 16[0092]a-cshow fitting210 includingedge212 at a flared end, and a slotted region to ensure a fluid tight fit after deployment and securement of the fitting210 to a vessel with a compression ring (not shown). As shown in FIG. 16c,the lower edge is advanced through thepuncture site214, and the fitting210 is rotated to advance the distal, flared end of the fitting into the vessel. Once in the vessel, a compression ring is advanced over the fitting210 and is locked in place with thetabs200 thereby securing the vessel wall between the distal, flared end of the fitting and the compression ring. The fitting210 includes multiple rows oftabs200 to accommodate various sized vessel walls. This feature is important when treating vascular diseases associated with thickening of the vessel wall.
• FIGS. 16[0093]d-eshow fitting220. In this configuration, a guidewire is inserted through the vessel wall and into the interior of the host vessel by puncturing the vessel wall with a needle and inserting the guidewire through the lumen of the needle. The needle is removed from around the guidewire after inserting the guidewire through the vessel wall. Aninsertion tubing222 containing acentral lumen224 follows the periphery of the flaredend226 and is adapted to pass a guidewire. The guidewire is fed through theinsertion tubing222 to facilitate the screwing of the fitting past the vessel wall. Theinsertion tubing222 extends approximately 40% to 80% around the flared end circumference. Alternatively, theinsertion tubing222 may be configured in sections extending around the circumference of the flared end such that a physician may determine how far around the flared end the guidewire must extend in order to rotate the flared end past the host vessel wall. Aslot228 through the distal flared end is adapted to accept the thickness of the vessel wall and enables the screwing of the fitting through the vessel wall. As the fitting220 is advanced over the guidewire and rotated, the fitting220 simultaneously expands the puncture through the vessel wall and inserts more of the distal flared end into the vessel interior. Once the flared end of the fitting220 is inserted into the host vessel interior, the guidewire is removed and the fitting220 is secured to the vessel wall using a compression ring and/or thermal securing. When using thermal securing, the distal flared end (at least the side facing the vessel wall) is made conductive and is attached to an energy source to heat the vessel and to thermally secure the fitting220 to the vessel wall.
• The fittings may be configured to incorporate electrodes to facilitate thermal securing of the fitting to the vessel wall. The electrodes may be fabricated from stainless steel, nickel titanium, platinum, platinum iridium, gold, titanium, tungsten, tantalum, or other conductive material and may also be fabricated to provide structural support to the bypass graft. Alternatively, the electrodes may be deposited (e.g. ion beam assisted deposition, sputter coating, solder, silk screen, pad printing, painting conductive epoxy, or other process) on the fittings and/or bypass graft such that the electrodes are thin and flexible and follow the contours of the fittings and/or bypass graft. The thermal securing properties may be the only attachment means required to provide a fluid tight bond between the fitting and the vessel wall. Alternatively, thermal securing may be augmented by attaching a compression ring as described above, applying adhesives to the bond, or suturing the fitting to the vessel wall. After securing the bypass graft to the fitting and advancing the fitting into the host vessel, the bypass graft and fitting combination may be attached to the host vessel wall.[0094]
• FIGS. 17[0095]a-bshow a fitting240 for performing an end-to-side anastomosis. Abypass graft16 is everted over the distal end of the fitting240. A retaininghousing242, similar to that shown in FIGS. 6e-f,is used to secure the bypass graft to the fitting. This retaininghousing242 permits radial expansion during placement over thebypass graft16 and fitting and has a preshaped memory to compress around the bypass graft and fitting240 to secure the bypass graft. This retaininghousing242 haspetals244 at its distal end, which compress into a low profile during delivery through a sheath and expand radially once deployed into thevessel38. The number ofpetals244 depends on the size of the bypass graft and the size of the host vessel. In this embodiment, eight petals are used. After advancing the fitting through a sheath, the fitting is advanced beyond the end of the sheath and is no longer constrained by the sheath, and expands towards its resting configuration. Then the bypass graft and fitting combination is gently retracted to engage the interior vessel wall at thepetals244. For mechanical securing, acompression ring246 is advanced over the fitting thereby compressing thevessel wall39 between thepetals244 of the retaining housing and thecompression ring246. The retaining housing may incorporate a threadedmechanism248 to screw on the compression ring and secure the compression ring relative to the retaining housing. The threads are oriented only along the sections of the retaining housing configured to engage the compression ring. The slotted regions enabling the retaining housing to radially expand and collapse do not include threads. Thecompression ring246 is alternatively locked in place using a screw mechanism, a ratchet mechanism, adhesives, sutures, or other attachment means to secure the compression ring in place. Thecompression ring246 incorporates two components: 1) a distal, flexible o-ring ordisk250 designed to produce a fluid tight seal and prevent damaging the vessel wall by excess compression; and 2) a proximal, morerigid locking ring252 used to maintain the position of the o-ring or disk relative to the vessel wall. Thelocking ring252 is designed to match the threads incorporated in the retaining housing. Mechanical securing may be replaced or augmented with thermal securing.
• FIGS. 18[0096]a-gshow a fitting260 used to produce an end-to-side anastomosis, especially for medium to small diameter vessels (e.g. peripheral vessels and coronary vessels). As shown in FIG. 18a,four petals are collapsed into a low profile for insertion through asheath262 during deployment into the vessel. Once positioned, thesheath262 is retracted enabling the petals to expand toward their resting shape. This fitting260 includes twopetals264 designed to extend axially along the vessel and pre-formed to contact the host vessel wall. The fitting also includes twoother petals266 and268 designed to extend radially around a portion of the vessel. The petals provide a structure to prevent the fitting from pulling out of the vessel, restrict rotation of the fitting relative to the graft, ensure the host vessel does not collapse or constrict at the anastomosis site, and provide a support to compress the vessel wall between fitting components. Thepetals266 and268 may be configured to return to a closed configuration in their resting state, as shown in FIG. 18f.Alternatively, thepetals266 and268 may be configured to expand beyond the closed configuration in their resting state, as shown in FIG. 18e.This configuration helps the fitting petals exert radial force on the host vessel to better support the fitting within the host vessel and keep the host vessel open at the bond interface. These end-side fittings may alternatively include more than4 petals. FIG. 18gshows an end-side fitting having two axially oriented petals,270 and four radially oriented petals,272. The petals,270,272 are configured to expand beyond the closed configuration in their resting state; alternatively, the petals may be configured to return to a closed configuration in their resting state. The fittings that produce end-to-side anastomoses may be configured to produce an angle (A) between thebypass graft16 and the interior of thehost vessel38.
• FIGS. 19[0097]a-fshow an end-to-side fitting290 that may be folded to insert through a sheath with a smaller diameter than the fitting. As shown in FIG. 19b,thefoldable fitting290 may be fabricated from a sheet of metal material that has been chemically etched, EDM, or laser drilled into the pattern shown. The opposite ends295 and297 of the fitting290 match so they may be bonded together to form the expanded cross-section shown in FIG. 19c.Alternatively, the fitting may be fabricated from a tubular metal material using chemical etching, EDM, laser drilling, or other manufacturing process to form the desired pattern.
• In FIG. 19[0098]a,thepetals292 are preshaped to expand radially outward once they have been deployed outside the introducing sheath. In this configuration the vessel wall can be compressed between thepetals292 and a compression ring. As shown in FIG. 19d,the fitting is designed to fold into a reduced diameter during deployment and expand toward its resting shape once positioned through the introducing sheath. The fitting includeslinks294 that are fabricated by reducing the thickness or width of the fitting material and act as hinges for the fitting to fold into a low profile. The foldable fitting embodiment shown in FIGS. 19a-fis designed with 6 sides connected withlinks293,294 so two adjacent sides are able to fold inward thereby reducing the diameter for insertion through the delivery system. The foldable fitting may further be configured so two more adjacent sides at the opposite end of the initially folded sides are able to fold inward and further decrease the profile for insertion through the delivery system. The foldable fitting may alternatively have more than6 sides and be configured so multiple adjacent sides fold inward to reduce the profile for introduction.
• In FIGS. 19[0099]e-f,the foldable fitting incorporates asynthetic graft material296 that is extruded, injection molded, or dipped onto the fitting290. The manufacturing process causes the graft material to fill slots andholes298 cut in the fitting290. This produces a more reliable bond between the synthetic graft material and the expandable, foldable fitting. Thecovered fitting290 will expand and fold as long as synthetic graft materials having a high percent elongation characteristic is chosen. The graft material may stretch along the folds incorporated in the fitting. A biological bypass graft (e.g. harvested vessel) may be sutured to theholes298 incorporated in the fitting. The manufacturing processes and materials for fabricating this fitting290 may also be used to fabricate end-to-end fittings by excluding the petals from the design. In addition, the foldable support structure may extend throughout the length of the bypass graft and be configured so that the sides rotate around the bypass graft at specific points to increase the axial flexibility but maintain the potential to fold into a reduced diameter.
• FIGS. 20[0100]a-bshow an end-to-side fitting310 having petals, and containing exposedelectrodes312 on the outside surface of the petals facing the vessel wall once deployed. Asignal wire314 is spot welded, crimped, attached using conductive adhesives, or soldered to provide an electrical connection between theelectrodes312 of the petals and a radiofrequency generator (not shown). The fitting310 is fabricated by extruding, injection molding, or otherwise applying a nonconductive, conformal coating (e.g. elastomer) over anelectrode structure316 configured to include petals. In a second operation, the outside surfaces of the petals are removed exposing theelectrodes312. The petals are preshaped so the outside surfaces defining the electrodes contact the vessel wall, once deployed. As shown in FIG. 20a,aconduction ring318 is placed into contact with theelectrode structure316 on the proximal end of the fitting and is bonded in place. Asignal wire314, used to transmit radiofrequency energy from a generator, is bonded to theconduction ring318. As a result, radiofrequency energy transmitted to theconduction ring318 will be routed to all electrodes positioned on the petals simultaneously. Alternatively,individual signal wires314 may be attached to eachpetal electrode312 and routed to a generator to independently energize each electrode.
• The[0101]signal wire314 may be fabricated from platinum, stainless steel, or a composite of materials (e.g. platinum and silver combined by a drawn filled tubing process). The composite signal wire uses the silver as the inner core to better transmit RF energy to the electrode and platinum to ensure biocompatibility. The signal wires may be fabricated with a circular, elliptical, rectangular (flat), or other geometry depending on the design of the electrode and space available in the delivery system. After thermal securing the bypass graft to the host vessel, the signal wire may be mechanically severed near the electrical connection using a pair of dikes. Alternatively, thesignal wire314 may incorporate a notch designed to separate when exposed to a desired amount of tension or torque, less than that required to dislodge the thermally secured bypass graft. Alternatively, the wire can be separated by transmitting pulses of radiofrequency or direct current energy through the signal wire capable of ionizing the signal wire and causing breakdown of the material. A notch may be incorporated in the signal wire to localize the breakdown point along the signal wire.
• FIGS. 21[0102]a-bshow an end-to-side fitting330 incorporating anelectrode structure332 for thermally securing the fitting330 to thevessel wall39. The fitting30 has a flared distal end with at least oneelectrode332 exposed along the outside surface of the fitting. A signedwire333 to transmit radio frequency energy from a generator may be attached toelectrode332. The at least oneelectrode332 extends around the fitting330 and has axial extensions adapted to orient the fitting along the vessel wall. The extensions provide an additional support structure to prevent rotation of the fitting relative to the vessel and reinforce the bond by using a mechanical securing mechanism such as a compression ring or other suitable means. The fitting330 is manufactured from a polymer dipped, deposited, coated, or injection molded over a conductive structure such that only the distal outside surface of the conductive structure is exposed. The electrical connection will be established prior to dipping or injection molding of the fitting. The distal end of the flared electrode structure has adetent334 to better secure the elastomer material to theelectrode structure332. The flared end of the fitting330 must be flexible enough to be gathered into a low profile for introduction through a sheath and must have enough stiffness to contact the vessel wall and produce a fluid tight seal once secured in place.
• FIGS. 21[0103]c-dshow another end-to-side fitting330 incorporating anelectrode332. This embodiment includes an elastomer orother coating336 around the distal, flared end of theelectrode332. Theelectrode332 is configured withpetals338 that collapse during deployment of the fitting into the vessel. Theelastomer coating336 masks the blood flow, maintains the collapsibility of the fitting, and helps ensure a fluid tight bond between the fitting and the vessel wall. Theelectrode332 is exposed on the outside surface of the distal, flared end of the fitting. Theelectrode332 provides mechanical support to the fitting and enables thermal securing of the fitting330 to thevessel wall39.
• FIGS. 22[0104]a-bshow an end-to-side fitting350 incorporating anelectrode structure332 that enables the fitting to collapse into a low profile for insertion through an introducing sheath having a smaller diameter than the fitting350. The distal flared end of theelectrode structure351 compresses forward and the body of the fitting folds into a low profile for insertion through a sheath. Once deployed outside the sheath, the fitting350 returns to its expanded, resting configuration. The flared, distal end contacts the interior surface of the vessel wall and provides a structure to compress the vessel wall using a compression ring. The electrode structure is fabricated from a conductive material (preferably but not limited to memory elastic materials) braided over a thermoplastic, thermoset plastic, silicone, or other material and is formed into a preshaped configuration having a flared end. The braided electrode structure may alternatively be composed of a memory elastic material such as nickel titanium for providing structural support intertwined with a good conductor such as platinum. Additionally, the braided material may be deposited with a conductive material to increase conduction. Since theelectrode structure351 is braided, the distal end of theelectrode structure351 is coated with an elastomer orother material352 to prevent unraveling of the braided material. Thiselectrode structure351 may also used to thermally secure the fitting to the vessel wall once radiofrequency energy is transmitted to the electrode structure from a generator.
• FIG. 23 shows an end-to-[0105]end fitting370 that permits retrograde blood flow through the anastomosis site. The fitting370 hasholes372 through the angled sections of the fittings to preserve fluid flow through the vessel distal and/or proximal, depending on the location of the fitting within the host vessel. The bypass graft andfitting combination374, after deployed within and attached to the vessel maintains blood flow through the stenosis as well as establishes a passage around thelesion376. The fitting370 maintains blood flow to branching vessels proximal to the anastomosis site.
• FIGS. 24[0106]a-bshow fitting370 attached to the vessel at two locations. The fitting370 is placed within the vessel and contacts the interior surface of the vessel along a substantial length. FIG. 24bshows that the fitting370 may incorporatebarbs382 to prevent axial dislodgment of the fitting from thehost vessel38. The barbs may also provide a support to secure a retaining ring or suture to mechanically secure the fitting to the host vessel. A second attachment is located at the insertion site through thevessel wall39. A compression ring or retaining ring may be used to compress thevessel wall39 around the fitting370 and prevent fluid from leaking at the insertion site. Electrodes may additionally or alternatively be positioned around the fitting at theinsertion site384 and/or at thedistal end386 of the fitting to thermally secure the fitting to the vessel wall and provide a fluid tight bond. The electrodes may be fabricated from stainless steel, nickel titanium, platinum, platinum iridium, gold, titanium, tungsten, tantalum, or other material and may also be fabricated to provide structural support to the bypass graft. Alternatively, the electrodes may be deposited (e.g. ion beam assisted deposition, sputter coating, pad printing, silk screening, soldering, or painting conductive epoxy) on the fittings and/or bypass graft, such that the electrodes are flexible and follow the contours of the fittings and/or bypass graft. Fitting370 is particularly useful for medium size diameter vessels (>3 mm) where synthetic bypass grafts are used to supplement the blood flow through the vessel or shunt the blood flow to other vessels or organs.
• FIGS. 24[0107]c-hshow additional end-end fitting embodiments that permit retrograde blood flow. The fitting380 incorporate a modification to provide a short proximal extension that contacts the vessel wall along the insertion site at the host vessel. This provides a structure to attach a compression ring and produce a fluid tight bond at the insertion site. A locking mechanism is incorporated in the fitting design to enable securing a compression ring to the fitting. Alternatively, FIGS. 24e-fshow the fitting380 may incorporate two electrodes,388,390 around the distal end and proximal extension of the fitting. An electrode may also be located around the leg of the fitting located at the insertion site. The electrodes,388,390 may incorporate holes to improve thermal securing of the electrodes to the host vessel wall.
• FIGS. 24[0108]g-hshow another end-end fitting385 that permits retrograde perfusion and incorporates electrodes,392,394 around the distal end and proximal extension of the fitting. This fitting also includes two separate lumens.Lumen396 connects blood flow from thebypass graft16 to the host vessel.Lumen398 connects blood flow between regions of the host vessel proximal to the anastomosis site and distal to the anastomosis site.
• The inventions described in this patent application describe embodiments that permit thermally securing bypass grafts to host vessels. The inventions require localized transmission of energy to precisely heat the interior surface of the host vessel and a support structure to maintain contact between the bypass graft and host vessel during and after the thermal securing process. The coagulation of tissue and shrinkage of blood vessels results from the application of heat and thermally secures the bypass grafts to the host vessel.[0109]
• A thermal securing mechanisms as shown in FIGS. 14 and 25 is used to increase the strength of the mechanical bond, and ensure a fluid tight seal between the bypass graft and host vessel. Alternatively, thermal securing may be solely used to bond the bypass graft fitting to the vessel wall. This feature may be adapted to all fittings. Thermal securing is accomplished by coagulating tissue to the electrodes and is enhanced by an induced shrinking of the heated tissue region producing an interference fit between the vessel and the fitting. These physiologic responses to heating produce a secure bond between the electrode and the vessel wall and prevent leaking around the fitting.[0110]
• Coagulating tissue to thermally bond a patch of porous material to the external surface of tissue has been described by Fusion Medical Technologies, Inc. (U.S. Pat. Nos. 5,156,613; 5,669,934; 5,690,675; 5,749,895; and 5,824,015). A sheet of collagen or similar porous material is placed over tissue and sufficient energy from a radiofrequency inert gas source is delivered over the patch to form coagulum at the tissue surface. The coagulum fills the pores of the external patch and cools to form a bond thereby producing hemostasis between the tissue and the external patch. The Fusion Medical product is suited for applications such as lung resections or reattaching transected vessels where direct exposure to the wound enables positioning the patch over the external surface of the tissue, and an energy source may be used to grossly apply heat over the exterior of the patch.[0111]
• Published studies evaluating the response of vessels (arteries and veins) to heat have focused on the ability to permanently occlude vessels. Veins have been shown to shrink to a fraction of their baseline diameter, up to and including complete occlusion, at temperatures greater than 70° C. for 16 seconds; the contraction of arteries was significantly less than that of veins but arteries still contracted to approximately one half of their baseline diameter when exposed to 90° C. for 16 seconds (Gorisch et al. Heat-induced contraction of blood vessels.[0112]Lasers in Surgery and Medicine.2:1-13, 1982; Cragg et al. Endovascular diathermic vessel occlusion.Radiology.144:303-308, 1982). Gorisch et al also observed vessel relaxation within 8 minutes after exposure to heat with arteries relaxing more than veins; even so, the final diameters of the contracted arteries and veins were less than their baseline diameters. Embodiments of the invention mitigate the concern for vessel relaxation by incorporating a spring mechanism in the fitting and/or electrode design to accommodate subtle changes in vessel diameter.
• Gorisch et al explained the observed vessel shrinkage response “as a radial compression of the vessel lumen due to a thermal shrinkage of circumferentially arranged collagen fiber bundles”. These collagen fibrils were observed to denature, thus shrink, in response to heat causing the collagen fibrils to lose the cross-striation patterns and swell into an amorphous mass. These published observations into the contraction of vessels due to heat provide evidence to the proposed invention of using radiofrequency energy to produce an interference fit between a contracted vessel and a fitting.[0113]
• FIG. 25 shows a schematic for a[0114]bypass graft16 incorporating two end-to-end fittings and containingelectrodes400 designed to thermally secure the bypass graft to the vessel wall. Theelectrodes400 are secured to the fitting and are bonded to signal wires,402 and404, which are routed to agenerator406. Radiofrequency or d.c. current is transmitted to the electrodes unipolar to an indifferentground patch electrode408 placed on the patient, or bipolar between the electrodes.
• Various features of the electrodes enhance the heating response and improve the bonding between the electrodes and the vessel wall. Contact between the electrode and the vessel is important to ensure an adequate bond when thermally securing the electrode to the vessel wall. The outer diameter of the electrode in its expanded configuration should exceed the inner diameter of the host vessel to ensure adequate contact between the vessel wall and the fitting.[0115]
• FIGS. 26[0116]a-bshow an end-to-end fitting420 incorporating anelectrode422 into the design. The fitting420 collapses into a low profile during insertion into the vessel and expand towards its resting state upon deployment into the vessel. Such an expandable, collapsible fitting helps ensure contact between theelectrode422 and the vessel wall despite any mismatching of the bypass graft size to that of the host vessel. The fitting may be extruded in a multi-layer configuration. The electrode may be braided into a mesh over aninitial polymer layer426. Asecond polymer428 may be extruded, injection molded, or dipped over the braided first layer. To expose theelectrode422, a section of the outer layer is removed. Alternatively, the section of exposed electrode may be masked when extruding, injection molding, or dipping the outer layer. Asignal wire424 is bonded to the braided mesh, before or after fabricating the outer layer, to produce an electrical connection that is routed to a generator.
• FIGS. 27[0117]a-bshow a bypass graft incorporating anelectrode430 that is designed to collapse into a low profile during deployment and expand to contact the vessel wall once inserted into the vessel. Theelectrode430 is attached to asignal wire432, which is used to connect the electrode to a generator434. Thiselectrode430 is fabricated from a mesh of memory elastic material formed over aninitial polymer layer436, and preshaped to have an expanded region as shown. The regions proximal and just distal to the expanded electrode have a tubular shape and are coated with a thermoplastic orthermoset insulative material438. This process forms a fitting incorporating an expandable, collapsible electrode that does not change the inner diameter of the bypass graft during or after deployment.
• Another important feature to thermally secure a fitting to a host vessel is the current density profile transmitted from an electrode to tissue. The configurations of the expandable retaining rings, previously discussed in FIGS. 5[0118]a-dand FIGS. 6a-d,make them more effective at thermally securing the retaining ring (electrode) and the bypass graft and fitting combination, to the vessel wall. These electrodes are designed with edges at the holes, notches, and slots cut in the ring. These holes, notches, and slots may be fabricated by laser drilling, EDM, milling, or other manufacturing process. Deposited electrodes, when used, may be applied in patterns that contain numerous edges. When radiofrequency energy is transmitted to these electrodes, the edges produce high current densities that locally heat the vessel wall. The small cross-sectional diameters of the conductive material forming the retaining rings ensures minimal depth of penetration, maintains focuses heating of the vessel wall, and helps to prevent damage to adjacent anatomy. In addition, the spaces defined by the electrode holes, notches, and slots provide a place for the vessel to shrink and coagulate. This increases the bond strength between the electrode and the vessel wall. The electrodes may additionally be covered with a porous material, such as collagen, fibrinogen, gelatin, and urethane, to further define a structure incorporating holes, notches, and slots for tissue to shrink and coagulate. The use of materials containing holes, notches and slots may also be used to encourage neointimal cell growth. Porous materials having a low melting point (e.g. 60° C.-120° C.) may be chosen to enhance thermal bonding between the bypass graft and host vessel wall. Heating such porous materials causes them to soften, reform and/or crosslink to coagulated tissue while heating the vessel wall with the electrodes.
• As previously discussed, electrodes may also be incorporated in the end-to-side fittings. The electrode features described above which improve thermal securing may be incorporated in the petals or flared regions of the end-to-side fittings. These features are designed to increase contact between the electrode and the interior of the vessel wall, provide a structure to localize bonding between the vessel wall and the electrode, and insulate the electrodes from blood flow.[0119]
• FIG. 28[0120]ashows cut-outareas450 oriented along the tear-awaysheath452 and distributed radially around thesheath452 that permit blood to flow through the cut-out areas in the sheath and past the distal lumen of the sheath. Alternative distributions and geometries for the cut-out areas may be chosen based on application and insertion requirements for the bypass graft. FIG. 28bshows a tear-away sheath incorporating ananchoring extension454 at the distal end of the sheath. Theextension454 is designed to maintain access between the tear-away sheath and the host vessel when the sheath is positioned perpendicular to the host vessel. The length of the sheath should be limited to that required to access the interior of the host vessel while ensuring short bypass grafts may be inserted past the distal end of the sheath, especially when the bypass graft has been secured at the opposite end. To make the sheath suitable for less invasive access, a long side arm extension to the sheath may be incorporated to support the sheath during manipulations. The side arm should also permit splitting into two halves to remotely tear the sheath away from the bypass graft.
• FIG. 29 shows a snap fitting[0121]460 designed to facilitate bonding the bypass graft to the fitting. Adistal piece462 of the snap fitting incorporates extensions464 designed to lock thedistal piece462 to mating teeth466 of the proximal snapfitting piece460. Theproximal piece460 is also tapered to accommodate a range of bypass graft diameters. The bypass graft is inserted through theproximal piece460 and everted over the external surface of the proximal piece; alternatively, the bypass graft is positioned over the exterior surface of theproximal piece460. Then, thedistal piece462 is advanced over the bypass graft and proximal piece interface, and is locked to the teeth thereby securing the bypass graft to theproximal piece460. Thedistal piece462 is configured for end-end anastomoses; however, it may be modified with features described below to accommodate end-side anastomoses. The bypass graft and snap fitting combination may be thermally secured to a host vessel by delivering radio frequency energy through the distal piece after placing the distal piece in contact with the vessel wall, as will be described below. Alternatively, an electrode secured to the proximal piece, or the proximal piece also functioning as the electrode may be used to thermally secure the host vessel to the bypass graft and snap fitting combination.
• FIGS. 30[0122]a-dshows an alternative snap fitting480. The distal and proximal pieces are integrated into one component. This adaptation facilitates manipulation of the bypass graft relative to the fitting since the operator only needs to hold the bypass graft and single fitting; otherwise, the operator needs to hold the proximal piece, distal piece, and bypass graft while securing the bypass graft to the fitting. Thedistal piece482 contains locking hinges484 designed to move axially alongrails486 incorporated in theproximal piece488. The locking hinges484 move along therails486 but are unable to be separated from theproximal piece488. One way to accomplish this is by making the distal end of the locking hinges, positioned inside the rail openings, wider than the rail openings. The distal ends of the locking hinges also have extensions that mate and lock teeth incorporated in the rails of the snap fitting. In operation, the bypass graft is positioned through the open snap fitting and is secured by closing the snap fitting. With the snap fitting open, the bypass graft is inserted through the lumen of theproximal piece488 and is advanced over the tapered end of thedistal piece482. Then, the snap fitting is closed by moving the proximal piece along the locking hinges of the distal piece thereby compressing the bypass graft between the proximal piece and distal piece. The ends of the locking hinges are secured to the mating teeth of the rails to secure the distal piece relative to the proximal piece. Thedistal piece482 as shown is configured for end-end anastomoses; however, it may be modified with features described below to accommodate end-side anastomoses. As stated previously, the distal piece or proximal piece may function as electrodes to permit thermally securing the fitting to the vessel wall.
• FIGS. 31[0123]a-dshow an alternative snap fitting500 that has acentral piece502 and a lockableouter piece504. The outer piece is composed of a single cylindrical component or two distinct sections that are designed to pivot about ahinge506; the hinge connects the central piece and the outer piece, using atab508, to facilitate manipulating the snap fitting and the bypass graft. With the snap fitting open, the bypass graft is fed over thecentral piece502 from the side of the snap fitting not containing thetab508 connecting thehinge506 to the central piece. Thetab508 is located on one side of the central piece to facilitate advancing the bypass graft over the central piece without having to cut an incision through the distal end of the bypass graft. After the bypass graft has been positioned over the central piece, the outer piece is closed together compressing the bypass graft between the outer piece and the central piece. A locking mechanism is designed at the contacting ends of the outer piece and is configured to bond the outer piece in a closed, cylindrical position to reliably secure the bypass graft to the snap fitting. This may be achieved by incorporating mating teeth on opposite ends of the outer piece tailored to interlock when the ends overlap. The outer piece of this snap fitting embodiment may function as at least one electrode for thermally securing the fitting to the vessel wall.
• FIG. 32[0124]a-bshow snap fitting520 includingpetals522 or other suitable modification. The fitting520 may be used to produce end-side anastomoses. Thepetals522 of the snap fitting520 may function as at least one electrode for thermally securing the fitting to the vessel wall.
• Experimental studies of thermal securing were conducted by positioning metallic fittings, into canine femoral arteries and veins during 3 experimental procedures. Signal wires were bonded to the metallic fittings and connected to a generator capable of delivering radiofrequency energy having a frequency of 500 kHz and a maximum power of 50 Watts. The generator was programmed to terminate radiofrequency energy delivery when impedance exceeded 300Ω, signaling completion of the thermal bond. Radiofrequency energy was delivered between each fitting and an indifferent ground patch electrode placed on the animals' thigh. Radiofrequency power ranged between 5 and 20 Watts for a duration of 5 to 60 seconds. The thermal anastomoses were acutely evaluated for leak resistance, patency, and tensile strength.[0125]
• All bypass grafts were patent after thermal securing to the host vessel as evidenced by injection of contrast solution, visualized using fluoroscopy, demonstrating continuous blood flow through the bypass grafts. The thermal securing mechanism resisted leaking at the fitting to host vessel interface as demonstrated by hemostasis when the bypass graft was clamped thereby increasing the blood pressure at the anastomoses. The tensile strength of the thermal anastomoses reached 2 lbs. As a result, thermal securing was effective at bonding bypass grafts to host vessels producing end-to-end anastomoses exhibiting a fluid tight bypass graft to host vessel interface capable of withstanding pressures exerted in the vessel.[0126]
• The above described embodiments of the invention are merely descriptive of its principles and are not to be considered limiting. Further modifications of the invention herein disclosed will occur to those skilled in the respective arts and all such modifications are deemed to be within the scope of the invention as defined by the following claims.[0127]

Claims (7)

1. A bypass graft system comprising:

a fitting defining an inner surface, an outer surface, at least two ends, and a compression mechanism adapted to attach a bypass graft to the fitting; and

at least one electrode functionally connected to the fitting and an energy source;

wherein the energy source is adapted to transmit energy to the electrode and cause functionally adjacent regions of tissue to rise in temperature.

2. A bypass graft system comprising:

a fitting defining an inner surface, an outer surface, at least two ends, and a compression mechanism adapted to attach the bypass graft to the fitting;

a sheath adapted for insertion through a puncture in a vessel wall and including a lumen for passing the bypass graft and fitting into the vessel interiors, the sheath adapted to split in two or more pieces for removal from around the bypass graft; and

at least one electrode connected to the fitting and to an energy source;

wherein the energy source is adapted to transmit electrical current to the electrode and cause thermal excitation of an adjacent region of tissue.

3. A system for securing a graft comprising;

a tubular structure having at least two ends, an inner surface, and an outer surface;

a first fitting attached to one end of the tubular structure and having a cross-section that substantially matches the cross-section of the tubular structure;

a second fitting attached to the other end of the tubular structure and having a cross-section that substantially matches the cross-section of the tubular structure;

a delivery mechanism adapted to access the lumen of the vessel and adapted to hold the lumen in an expanded orientation, the delivery mechanism adapted to functionally cooperate with the fittings and tubular structure in order for the fittings and tubular structure to be inserted through an opening established in the vessel;

at least one first electrode associated with the first fitting adapted to thermally secure the first fitting to a vessel at the one location; and

at least one second electrode associated with the second fitting adapted to thermally secure the second fitting to the vessel at a second location.

4. The system ofclaim 3 wherein the fitting further includes more than two ends and a first electrode is bonded to one end; and

the bypass graft attached to the fitting at one end;

wherein the first electrode and second electrode are adapted to thermally secure the fitting to the vessel at one or more ends.

5. A bypass graft system comprising;

a fitting attached to the bypass graft, the fitting including a flared distal end and

at least one electrode associated with the flared distal end.

6. A bypass graft reinforcing structure comprising;

a tubular structure with an inner surface, outer surface, and two ends;

a first fitting attached to the tubular structure at one end;

a first compression mechanism adapted to secure a bypass graft to the first fitting;

a first electrode associated with the first fitting, the first electrode adapted to thermally secure the bypass graft and the tubular structure at one end;

a second fitting attached to the tubular structure at one end;

a second compression mechanism adapted to secure the bypass graft to the second fitting; and

a second electrode associated with the second fitting, the second fitting adapted to thermally secure the bypass graft and the tubular structure at the second end.

7. A bypass graft system comprising:

at least one fitting defining an outer surface, an inner surface and at least two ends;

at least one compression mechanism adapted to attach a graft to the at least one fitting;

at least one electrode associated with the at least one fitting, the at least one electrode adapted to transmit thermal energy to at least a region of tissue;

at least one current carrying member attached to the at least one electrode and adapted to be separated from the at least one electrode; and

a generator connected to the at least one current carrying mechanism, the generator adapted to transmit an electrical current to the at least one electrode and cause a region of tissue adjacent the at least one electrode to rise in temperature and become secured to one or more members or body regions.

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