WO2000056226A1 - Chirurgie vasculaire - Google Patents

Chirurgie vasculaire Download PDF

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Publication number
WO2000056226A1
WO2000056226A1 PCT/IL1999/000670 IL9900670W WO0056226A1 WO 2000056226 A1 WO2000056226 A1 WO 2000056226A1 IL 9900670 W IL9900670 W IL 9900670W WO 0056226 A1 WO0056226 A1 WO 0056226A1
Authority
WO
WIPO (PCT)
Prior art keywords
graft
connector
spikes
spike
tip
Prior art date
Application number
PCT/IL1999/000670
Other languages
English (en)
Inventor
Amir Loshakove
Ido Kilemnik
Dvir Keren
Original Assignee
By-Pass, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from IL12906799A external-priority patent/IL129067A0/xx
Priority claimed from PCT/IL1999/000285 external-priority patent/WO1999062408A1/fr
Priority claimed from PCT/IL1999/000284 external-priority patent/WO1999062415A1/fr
Application filed by By-Pass, Inc. filed Critical By-Pass, Inc.
Priority to JP2000606135A priority Critical patent/JP2002538925A/ja
Priority to US09/936,806 priority patent/US7063711B1/en
Priority to AU15831/00A priority patent/AU768923B2/en
Priority to KR1020017011929A priority patent/KR20020067616A/ko
Priority to IL14546099A priority patent/IL145460A0/xx
Priority to EP99958467A priority patent/EP1171042A1/fr
Priority to BR9917217-8A priority patent/BR9917217A/pt
Priority to MXPA01009475A priority patent/MXPA01009475A/es
Priority to NZ514744A priority patent/NZ514744A/xx
Priority to CA002366703A priority patent/CA2366703A1/fr
Priority to AU15835/00A priority patent/AU1583500A/en
Priority to US09/936,789 priority patent/US7060084B1/en
Priority to BR0009172-3A priority patent/BR0009172A/pt
Priority to PCT/IL1999/000674 priority patent/WO2000056223A1/fr
Priority to BR0016251-5A priority patent/BR0016251A/pt
Priority to AU33136/00A priority patent/AU3313600A/en
Priority to US09/936,805 priority patent/US6979338B1/en
Priority to IL14543100A priority patent/IL145431A0/xx
Priority to CA002366708A priority patent/CA2366708A1/fr
Priority to EP00911144A priority patent/EP1171044A1/fr
Priority to NZ514745A priority patent/NZ514745A/en
Priority to CN00805205A priority patent/CN1353594A/zh
Priority to MXPA01009472A priority patent/MXPA01009472A/es
Priority to AU33138/00A priority patent/AU769269B2/en
Priority to KR1020017011866A priority patent/KR20010113767A/ko
Priority to JP2000606137A priority patent/JP2002538926A/ja
Priority to US09/936,796 priority patent/US6726704B1/en
Priority to PCT/IB2000/000302 priority patent/WO2000056227A1/fr
Priority to BR0016247-7A priority patent/BR0016247A/pt
Priority to PCT/IL2000/000609 priority patent/WO2001041623A2/fr
Priority to CA002393508A priority patent/CA2393508A1/fr
Priority to JP2001542802A priority patent/JP2003515416A/ja
Priority to EP00964605A priority patent/EP1259169A2/fr
Priority to EP00964603A priority patent/EP1237485A2/fr
Priority to PCT/IL2000/000611 priority patent/WO2001041624A2/fr
Priority to AU75525/00A priority patent/AU7552500A/en
Priority to IL15000300A priority patent/IL150003A0/xx
Priority to IL15005100A priority patent/IL150051A0/xx
Priority to AU75527/00A priority patent/AU7552700A/en
Priority to CA002393486A priority patent/CA2393486A1/fr
Priority to JP2001542803A priority patent/JP2004513670A/ja
Publication of WO2000056226A1 publication Critical patent/WO2000056226A1/fr
Priority to HK02103911.8A priority patent/HK1042030A1/zh
Priority to US10/459,407 priority patent/US20040073247A1/en
Priority to US10/668,059 priority patent/US20050101983A1/en
Priority to AU2004201487A priority patent/AU2004201487A1/en
Priority to US11/210,554 priority patent/US20050283188A1/en

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/11—Surgical instruments, devices or methods, e.g. tourniquets for performing anastomosis; Buttons for anastomosis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/0057—Implements for plugging an opening in the wall of a hollow or tubular organ, e.g. for sealing a vessel puncture or closing a cardiac septal defect
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/064—Surgical staples, i.e. penetrating the tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/068—Surgical staplers, e.g. containing multiple staples or clamps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/0057—Implements for plugging an opening in the wall of a hollow or tubular organ, e.g. for sealing a vessel puncture or closing a cardiac septal defect
    • A61B2017/00637—Implements for plugging an opening in the wall of a hollow or tubular organ, e.g. for sealing a vessel puncture or closing a cardiac septal defect for sealing trocar wounds through abdominal wall
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/0057—Implements for plugging an opening in the wall of a hollow or tubular organ, e.g. for sealing a vessel puncture or closing a cardiac septal defect
    • A61B2017/00646—Type of implements
    • A61B2017/00663—Type of implements the implement being a suture
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/0057—Implements for plugging an opening in the wall of a hollow or tubular organ, e.g. for sealing a vessel puncture or closing a cardiac septal defect
    • A61B2017/00646—Type of implements
    • A61B2017/00668—Type of implements the implement being a tack or a staple
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00831—Material properties
    • A61B2017/00867—Material properties shape memory effect
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/064—Surgical staples, i.e. penetrating the tissue
    • A61B2017/0641—Surgical staples, i.e. penetrating the tissue having at least three legs as part of one single body

Definitions

  • the present invention relates to performing anastomosis of blood vessels.
  • anastomosis Connecting two blood vessels, anastomosis, is an important surgical technique for reconstructive, therapeutic and cosmetic surgery.
  • the gold standard of anastomosis is manual suturing of the two blood vessels in a side to side, end to end or end-to-side configuration.
  • the anastomosis is sealed by stapling the graft to the aorta, while pressing both aorta and graft against an anvil.
  • the anvil is inserted into the aorta for the stapling and then removed, possibly by taking the anvil apart.
  • the end of the graft is everted over a ring-shaped anvil, so that the anvil is outside of the blood vessel at all times.
  • bypass surgery has been performed using minimally invasive (key-hole) surgery.
  • a small hole is made in the chest, instead of cracking open the ribs, and the mammary arteries (e.g., LIMA, RLMA) are used for bypass grafts.
  • the suturing and/or stapling is performed using tools, for example as described above.
  • a tunnel is excavated within tissue (outside the vessel) from one side of the occlusion to the other side of the occlusion, and a stent or a stent/graft may be placed within the tunnel.
  • a conveniently located vein or graft is attached to the occluded vessel and two side-to-side anastomosis are created between the occluded vessel and the vein or graft bypassing the occlusion.
  • the distal and proximal portions of the vein are closed in one of a variety of manners.
  • the connection between the vein and the artery may be by welding the two blood vessels, or by using one of a variety of connectors that are suggested.
  • One of the disclosed connectors comprises two springs separated by a short segment of a possibly unstented graft.
  • the springs have the form of an inverted funnel, so that the two blood vessels are urged together.
  • various techniques and/or devices are suggested for stopping the surrounding tissue from compressing the connection between the vein and the artery.
  • One of the purposes of the various types of connectors is to maintain the two blood vessels near each-other, either in contact or by compressing tissue between them, presumably so no blood will leak from the connection between the connector and the blood vessels.
  • a stent In a TIPS procedure, a stent is placed into a passage precutaneously forced, opened or excavated between a portal vein and a hepatic vein.
  • the relative location of the blood vessels is maintained by the existence of relatively solid tissue surrounding and between the two blood vessels.
  • a method for reducing the complexity of performing a bypass surgery.
  • a graft is precutaneously brought to the aorta and pushed out of an incision in the aorta near a site of a bypass surgery.
  • a keyhole opening is made in the chest to bring a tool to suture or staple the graft to the aorta and to the coronary which is to be bypassed.
  • a typical treatment procedure in these cases is to perform a bypass of the abdominal aorta, of the femoral artery or perform a femoral-popliteal bypass.
  • An aspect of some preferred embodiments of the invention relates to a self-locking anastomosis device comprising a collar portion and a spike portion comprising a plurality of interconnected spikes, both of which portions are preferably formed of a sheet material or a tube material, preferably the same material.
  • the spike portion locks against the collar portion so that once the anastomosis device is deployed, it does not open by itself.
  • the anastomosis device is formed of two components, a spike section and a collar section. Alternatively, the two sections may be integrated in a single component.
  • the lock includes some flexibility, to example to allow relative axial motion of the two sections.
  • An aspect of some preferred embodiments of the invention relates to an anastomotic connector having a spring element for allowing relative motion between a two vessels connected by the anastomotic connector.
  • a plurality of spring elements are provided so that different parts of the vessels have a different amount of relative motion.
  • all the springs are referenced to a single collar attached to one of the vessels. However, this is not essential and different springs can be referenced to different ones of the vessels and/or to different portions of the connector.
  • the springs allow relative motion between spikes which engage one vessel and the collar which is coupled to a second vessel.
  • the relative motion may be limited to small parts of the anastomosis connection.
  • each spike by providing each spike with a spring, differences in the thickness of tissue engaged by the spike are compensated for by the spring.
  • the spring allow the areas of contact between the vessels to be urged against each other.
  • the spring element may be an explicit spring element, for example formed as part of a spike.
  • the spring may be functionally included in another structure, for example a locking element for interlocking the two parts of a two part anastomotic device.
  • An aspect of some preferred embodiments of the invention relates to forming holes in small vessels, such as coronary vessels.
  • a small hole is formed by first grabbing a small section of a vessel (e.g., a coronary) and then cutting the grabbed section.
  • the grabbing and cutting may be by separate elements of a hole puncher or by a single element.
  • the grabbed section has a radius smaller than twice the thickness of the coronary.
  • the grabbing element is retracted from the vessel, so that the grabbed section of the coronary is distanced from the opposite side of the coronary.
  • An aspect of some embodiments of the invention relates to forming holes in a coronary vessel by cutting along a circumference of a desired hole.
  • a rotating cutting device is provided having a central grabber and a cutting edge, preferably in the form of a spike, on its circumference.
  • the grabber is a hollow tube for providing vacuum.
  • the grabber is a mechanical grasper. In use, the grabber grabs the vessel, so that the spike penetrates the vessel wall. The spike-carrying portion is then rotated, so that a section of the vessel wall is cut off.
  • An aspect of some preferred embodiments of the invention relates to a self-retracting tip for a punch.
  • the tip retracts prior to the hold being punched in the blood vessel.
  • the punching action is caused by the tip retracting.
  • the tip retracts it cannot easily advance, thereby providing an additional safety feature.
  • the hole punch comprises two elliptical surfaces, which surfaces are not parallel to each other. Preferably, a small angle, such as 5° is defined between the surfaces.
  • at least one of the surfaces is not planar, for example including a protrusion to better engage the blood vessel being punched through.
  • An aspect of some preferred embodiments of the invention relates to a hole puncher, in which the punching action is achieved by non-axial manipulation of the puncher.
  • the hole puncher is adapted for key-hole surgery.
  • the puncher has an axial handle.
  • the puncher has a revolver grip.
  • the punching is achieved by squeezing on the handle of the hole-puncher.
  • An aspect of some preferred embodiments of the invention relates to a set of tools for anastomosis connection, in which the tool surrounds the graft. Once the graft is attached, the tool can be removed from the graft. In some embodiments of the invention, there is a slit in the side of the tool, through which the graft is inserted and/or removed. Alternatively or additionally, the tool can open or be taken apart.
  • the tool includes a peg, which, when a portion of the tool is pulled over the peg, splits the tool portion apart.
  • the tool is pre-split or at least perforated, however this is not essential.
  • a knife is provided, which knife rips the tool portion axially.
  • the knife and/or peg are stationary and the tool portions moves relative thereto.
  • the knife or peg are moved.
  • the tool includes a rigid portion which prevents the separation of the pre-spilt tool.
  • this rigid portion includes an opening, which, once the pre-split tool is retracted to the opening, allow the tool to spilt, so that the graft can be removed from the enclosing tool.
  • Exemplary tools in such a kit are one or more of an anastomosis maker, an graft everter and an anastomosis mounter. These tools may comprise a single tool with different attachments.
  • the tools are adapted for a keyhole approach.
  • the tools are adapted for a transvascular or an endoscopic approach.
  • the tool is cut open using an external tool, such as a knife.
  • a rip cord is used to slit open the tool.
  • the connector includes at least one (transaxial) thickening, preferably on a spike.
  • This thickening is preferably used to pull the connector away from the blood vessel, thereby piercing the blood vessel using hooked spikes on the other side of the connector.
  • the thickening is used to push the connector forwards, into the blood vessel.
  • the spike on which the thickening is formed is elastic, super elastic or otherwise moves out of the connector plane when the anastomosis device is employed. Thus, the anastomosis device is disconnected from a deployment tool by allowing or causing the spikes to bend out of an axial engagement by the tool.
  • An aspect of some preferred embodiments of the invention relates to a method of mounting a spike-including anastomosis device on a graft, without a separate step of everting the graft.
  • the graft is transfixed on the spikes in a first configuration of the spikes, while maintaining the graft in a substantially neutral configuration (e.g., uneverted).
  • the spike configuration is changed, for example rotated outwards, so that the spikes are in a better position to engage a second vessel when the anastomosis is performed.
  • the graft is advanced towards the second vessel, the graft is preferably everted by the contact.
  • the spikes are hooked so as to easily penetrate the graft when they are pointed at the graft and to easily engage the second vessel when they are rotated away from the graft.
  • An aspect of some preferred embodiments of the invention relates to a method of everting a graft, in which the graft end is rolled up back over the portion of graft adjacent to the graft end.
  • the end of the graft is grasped and then pulled back over the graft.
  • the graft is enclosed in a tube over which the end is everted.
  • free motion between the tube and the graft are allowed.
  • the end of the tube serves as a pivot for folding back of the graft.
  • the eversion process is mechanical and not directly manual.
  • An aspect of some preferred embodiments of the invention relates to a method of everting an end of a graft, in which the near end is rolled forward, over the graft, towards the distal end of the graft.
  • the graft is mounted on a tube or inside of it and the near end of the graft is pushed, preferably in small increments, towards the distal end of the graft.
  • the near end is engaged and pushed.
  • An aspect of some preferred embodiments of the invention relates to a method of shaping a portion of a graft, especially an end, but possibly also a middle of a graft.
  • this method is used for simulating the eversion of a graft without everting the graft, by causing an end of the graft to thicken.
  • the graft is a mammary artery.
  • the graft is thickened at its end by axially compressing the graft end.
  • the axial compression utilizes a form inside the graft, to set (increase, decrease or maintain) the graft inner diameter.
  • the compression may be used to form an end that is perpendicular to the axis or the compression may be constrained to form other shapes, such as a saddle shape to match a profile of a coronary, or to form an oblique end.
  • the transfixing of the graft thickening by the anastomosis connector assists in maintaining its shape.
  • the thickening causes some of the intima to be presented along the end if the graft, assisting in performing an intima-to-intima anastomosis connection and/or an adventizia to adventizia connection and/or matching up of other vascular layers.
  • the thickened portion is transfixed by spikes of an anastomosis connector along paths parallel to the graft axis.
  • An aspect of some preferred embodiments of the invention relates to creating an everted graft end having an oblique angle to the graft axis. Direct eversion at an oblique angle may be difficult.
  • an anastomotic connector has spikes that are pre-bent so that their tips are at an angle substantially parallel to the surface of the other vessel.
  • an aspect of some preferred embodiments of the invention relates to a form of a spike- tip useful in preventing the spike from advancing too deeply.
  • the spike tip is split, for example into two or three tines (e.g., like a tuning fork).
  • the spike advances only until the spilt location meets the aorta.
  • the spilt defines a wide angle between the tines, to prevent compression of tissue between the tines.
  • kits for performing bypass procedures in a peripheral (non-coronary) vessel for example in the leg or the abdominal aorta.
  • a kit includes a graft having an anastomotic connector mounted at each end thereof and a guide for guiding the graft between two anastomosis connection locations.
  • the guide comprises a guide wire.
  • the guide is a rigid guide.
  • the guide is a deflectable guide.
  • An aspect of some preferred embodiments of the invention relates to a method of releasing an elastic or super-elastic device from a constraint, in which removing an upper constraints allows the device to deform and detach itself from protrusions defined on the lower constraint.
  • An aspect of some preferred embodiments of the invention relates to a self everting anastomosis connector.
  • the connector is pre- stressed and forward spikes thereof are inserted into a graft. When the spikes are released, they rotate in a plane perpendicular to the vessel axis, everting the vessel.
  • the connector may include additional crimping elements (e.g., as part of a flange), which crimp the end of the vessel between them and when they are deformed, pull the end of the vessel along, for example to form an eversion. Necrosis at the end of the vessel may be considered insignificant in some embodiments of the invention.
  • an anastomotic connector for connecting a graft to a target vessel, comprising: a thin collar section, adapted to engage a portion of the graft; and a separate spike section, adapted to mount on said collar section and comprising a plurality of spikes, each of said spikes adapted to transfix said graft.
  • the connector comprises at least one locking element for interlocking said spike section and said collar section.
  • said locking element is formed on said collar portion.
  • said locking element mates with an aperture defined by said spike section.
  • said locking element provides a spring- action, which action resists relative motion axial between at least part of said spike section and at least part of said collar section, with a force dependent on the range of motion.
  • said spike section comprises a super- elastic material.
  • said spikes are pre-bent in a hook shape, such that said hook shape is adapted to engage the target vessel.
  • said collar element comprises a plurality of flange elements proximal to said target vessel.
  • said flange elements define apertures for said spike elements to pass through.
  • said flange elements include at least one opening in their perimeter, wide enough for one of said spikes to be brought in through.
  • said collar section defines a cylindrical volume.
  • said collar section is adapted to form a perpendicular anastomosis.
  • said collar section is adapted to form an oblique anastomosis.
  • an anastomotic connector for connecting a graft to a target vessel, comprising: a base for engaging said graft; a plurality of spikes for transfixing said graft and engaging said target vessel; and at least one spring element attached to at least one of said spikes, which spring element couples a connection between said spike and said base.
  • said spikes and said base form a single element.
  • said spikes and said base form two separate elements.
  • said spring comprises a flat coil spring.
  • said spring comprises a leaf spring.
  • said at least one spring comprises at least two springs in series.
  • each of said spikes has at least one independent associated spring.
  • said connector is configured for performing an oblique anastomosis.
  • said connector comprises at least one tab associated with one spike of said spikes, for moving said spike.
  • said tab is adapted for retracting said spike.
  • said tab is adapted for advancing said spike.
  • apparatus for delivering a graft to an anastomosis comprising: at least two tube-like elements, each defining an aperture adapted for inserting said graft such that the graft exits through a first end of said tube-like elements; at least one separator element mounted on at least one of said tube-like elements for splitting the other of said tube like elements, so the graft can be removed through a resulting slot, which slot spans said first end and said aperture.
  • said at least one separator comprises a knife which cuts said slit.
  • said at least one separator comprises a spreader which widens an existing slit in said tube to form said slot.
  • the apparatus comprises an outer tube which prevents said tube from splitting unless it is sufficiently retracted.
  • said tube-like elements are adapted to carry an anastomotic device between them.
  • a method of removing a graft delivery tool from an enclosed graft comprising: splitting apart said tube, to form a slot using a slot- forming element; and removing said graft through said slot.
  • said slot-forming element comprises a knife that splits said tube.
  • said slot-forming element comprises a spreader that widens an existing slit in said tube.
  • the method comprises retracting at least one tube that encloses said graft.
  • said retracting urges said tube against a slot forming element.
  • the method comprises moving said slot- forming element relative to said tube, to form said slot.
  • an anastomosis connector comprising: a ring shaped base having an axis; at least one plurality of spikes on one side of said ring; and at least one transaxial thickening in at least one of said spikes, distanced from said ring.
  • the connector comprises a second plurality of spikes pointing in an opposite direction from said first set of spikes.
  • said thickening comprises a point where said spike splits into tines.
  • said tines are shorter than a thickness of a target blood vessel for which the connector is designed.
  • said at least one plurality of spikes do not apply radial pressure towards or away from said ring, once deployed.
  • a method of containing and releasing an anastomotic connector having a thickening comprising: containing said connector between two tubes, said thickening being constrained from axial motion by at least one protrusion defined on at least one of said tubes; and removing at an outer one of said tubes, such that the connector deforms and the thickening is not constrained by said at least one protrusion.
  • a method of performing an anastomosis between a graft and a target vessel comprising: inserting an anastomosis connector into the target vessel; releasing at least one forward spike of said connector; retracting said connector such that said forward spike engages said target vessel; and completing said anastomosis.
  • completing said anastomosis comprises releasing at least one backward spike of said connector to engage said target vessel.
  • completing said anastomosis comprises locking said spike to a part of said connector other than said spike.
  • completing said anastomosis comprises releasing said spike to retract towards to a part of said connector other than said spike.
  • a punch mechanism for punching a hole in a blood vessel comprising: a sharp tip adapted for puncturing said blood vessel; a shaft having said tip at one end thereof; a first widening element distal to said tip ; and a second widening element distal to said first widening element, said first and second widening elements defining a narrowing between them, which narrowing is adapted to contain a punctured blood vessel wall; and a coupling element for coupling retraction of said tip with a relative motion of said widening elements, which relative motion is used to contract said narrowing.
  • said tip retracts into said first widening, thereby pulling said first widening element towards said second widening element.
  • said tip is mounted on a tip-shaft and said tip is retracted by retracting the tip-shaft and wherein said tip shaft is coupled to said shaft, such that after sufficient retraction of said tip shaft, said tip shaft engages said shaft and retracts it.
  • a method of everting a graft comprising: grasping said graft between an internal mandrel and an outer tube; and pushing an end of said graft back over said graft.
  • the method comprises repeating said pushing a plurality of times to achieve a desired amount of eversion.
  • pushing said end of said graft comprises everting the end over said outer tube.
  • a graft everter comprising: a tip adapted for mounting an end of said graft thereon; a graft stop adapted for stopping an advance of said graft end over said tip; and a plurality of expanding fingers disposed between said graft stop and said tip, said fingers having an expanded state in which they have an external diameter larger than said tip and larger than said graft and an unexpanded state in which the diameter does not suffice to engage said graft.
  • a method of mounting an anastomosis connector having spikes with tips that bend out of a lumen of said connector, on a graft comprising: maintaining said at least some of said spikes in a twisted configuration such that tips of said spikes bend into the lumen; transfixing said graft on said tips; and changing the configuration of said tips to bend out.
  • changing the configuration comprises releasing said spikes.
  • a method of simulating eversion of a graft comprising: compressing an end of said graft into a form to provide a thickening of said end; and transfixing said thickening with at least one spike of an anastomosis connector.
  • said graft comprises a mammary artery.
  • said transfixing comprises transfixing along an axis of said graft.
  • said transfixing comprises transfixing oblique to an axis of said graft.
  • said transfixing comprises transfixing perpendicular to an axis of said graft.
  • said form comprises an inner mandrel.
  • said form defines, on said graft, a flat end surface for said thickening.
  • said form defines, on said graft, an oblique end surface for said thickening.
  • said form defines, on said graft, an non-planar end surface for said thickening.
  • a method of transfixing a connector on a graft comprising: widening a radius of an end of the graft; advancing at least one spike of said connector, parallel to said graft, such that it transfixes said widened area; and bending at least an end of said spike to form a hook.
  • a kit for a bypass procedure comprising: at least one graft having anastomosis connectors mounted on two ends thereof, said graft and said connectors adapted for a peripheral bypass procedure; and at least one guide wire attached to one end of said graft.
  • said connectors are embedded in said ends of said graft.
  • an oblique hole punch comprising: a shaft; a first non-circular edge oblique to said shaft at a first angle; a second non-circular edge oblique to said shaft at a second angle; and means for reducing a gap between said tow edges, so as to cut through vascular tissue placed between them.
  • said two angles are different.
  • said two angles are the same.
  • a penetrating punch for punching holes in a blood vessel during a keyhole procedure, comprising: a tip for puncturing said vessel; a rigid handle, adapted for keyhole surgery and coupled to said tip, for controlling a spatial position of said tip; two surfaces for receiving the walls of the vessel surrounding said puncture; and means for bring said surfaces together for punching said hole.
  • said tip is smooth.
  • said tip is axially grooved.
  • a method of heat-treating an anastomosis connector comprising: fitting a cut connector into a mold; fixing said mold to bend both forward and backwards spikes of said connector into a desired configuration; and heat-treating said fixed connector, thereby training it to said configuration.
  • Figs. 1A-1D schematically illustrate two parts of a two part anastomotic device of a preferred embodiment of the present invention, in isometric-perspective and in cut-through views;
  • FIG. 2A-2F schematically illustrate the operation of the device of Figs. 1A-1D, in accordance with a preferred embodiment of the invention
  • Figs. 3A and 3B are plan layouts of the two parts of the anastomotic device of Figs. 1A-1D, in accordance with a preferred embodiment of the invention
  • Figs. 4A-4D illustrate a method of retracting a ring portion of the anastomosis device of Figs. 1A-1D, in accordance with a preferred embodiment of the invention
  • Fig. 5 is a plan layout of a one piece anastomosis device, in accordance with a preferred embodiment of the invention
  • Figs. 6A and 6B are side cut-through images of an anastomosis area, showing a method of performing an anastomosis using the device of Fig. 5;
  • Fig. 7A is a schematic illustration of a splayed spike tip configuration, in accordance with a preferred embodiment of the invention.
  • Fig. 7B is a side cut-through view of a connector including the configuration of Fig. 7 A, deployed in an aorta, in accordance with a preferred embodiment of the invention
  • Fig. 8A is a plan layout of an aortic anastomotic connector in accordance with a preferred embodiment of the invention
  • Fig. 8B is a top view of the connector of Fig. 8 A, in a resting state;
  • Fig. 8C is an enlargement showing the meeting of two spikes from opposing sides of the connector
  • Fig. 8D is a view through line A-A of Fig. 8B, showing the relative placement of the spikes from two sides of the anastomosis device, in a resting state;
  • Fig. 9A and 9B show a mold suitable for training the anastomosis device of Figs. 8 A-
  • Fig. 10 is a flowchart of an exemplary process of keyhole bypass, in accordance with a preferred embodiment of the invention
  • Fig. 11 is a schematic illustration of a scaffold tool, which holds various other tools during a bypass procedure, in accordance with a preferred embodiment of the invention
  • Figs. 12A-12D illustrate a process of using a grab-and-cut punch, in accordance with a preferred embodiment of the invention
  • Figs. 13A-13D illustrate a process of using a rotating spike hole puncher, in accordance with a preferred embodiment of the invention
  • Figs. 14A-14E illustrate a process of using an anvil hole puncher, in accordance with a preferred embodiment of the invention
  • Figs. 15A-15D illustrate a hole puncher designed to be inserted in the scaffold tool of Fig. 11, and its use in accordance with a preferred embodiment of the invention
  • Figs. 16A and 16B illustrate in perspective view and in perspective cut-open view, respectively, a tip-retracting hole punch, in accordance with a preferred embodiment of the invention
  • Fig. 17 is a cut-open perspective view of a tip retracting hole punch, in accordance with an alternative preferred embodiment of the invention.
  • Fig. 18 shows an assembled and a disassembled oblique hole puncher, in accordance with a preferred embodiment of the invention
  • Fig. 19A is a schematic illustration of an alternative oblique hole puncher in accordance with another preferred embodiment of the invention
  • Fig. 19B shows two views of the tip of the puncher of Fig. 19A;
  • Figs. 20A-20D illustrate a connector mounting method in accordance with a preferred embodiment of the invention
  • FIGs. 21A-21E illustrate a graft everter, in accordance with a preferred embodiment of the invention
  • Fig. 22 is a schematic cut-through illustration of an alternative graft everter, in accordance with a preferred embodiment of the invention
  • Figs. 23A-23G illustrate a method of transfixing a blood vessel by twisting spikes of a connector, in accordance with a preferred embodiment of the invention
  • Figs. 24A-24E illustrate a method of simulating an eversion, especially for a mammary artery, in accordance with a preferred embodiment of the invention
  • Fig. 25 A is a close-up of the scaffold tool of Fig. 11 when a combination graft holder and connector holder is inserted therein, in accordance with a preferred embodiment of the invention
  • Fig. 25B is a perspective view of Fig. 25 A;
  • Fig. 26 shows the situation after a tip the scaffold of Fig. 11 is retracted, showing spikes that engage the target vessel;
  • Fig. 27 shows only one layer of the combination of Fig. 25A, emphasizing a pre- formed slit in the layer, a knife and protrusions;
  • Fig. 28 is a cut-through view of the scaffold of Fig. 11, showing a peg or a cone which splits apart the layer of Fig. 27when the layer is retracted sufficiently;
  • Figs. 29A-29F illustrate an alternative connector delivery system using a peg-based splitting mechanism, in accordance with a preferred embodiment of the invention
  • Figs. 30A-30D which correspond to Figs. 1A-1D illustrate an anastomosis connector adapted for oblique connections, in accordance with a preferred embodiment of the invention
  • Fig. 31 A which corresponds to Fig. 2F shows the connector of Figs 30A-30D, during deployment, in accordance with a preferred embodiment of the invention
  • Fig. 3 IB which corresponds to Fig. 2D, shows a completed oblique anastomosis, in accordance with a preferred embodiment of the invention
  • Figs. 32A and 32B which correspond to Figs. 3A and 3B show a layout view of the connector of Figs 30A-30D;
  • Figs. 33 A and 33B illustrate a method of mounting an oblique connector on a graft, in accordance with a preferred embodiment of the invention
  • Figs. 34A-34F illustrate a self-everting connector and a method of deploying such a connector, in accordance with a preferred embodiment of the invention.
  • Fig. 35 illustrates a graft having an anastomosis connector embedded therein, in accordance with a preferred embodiment of the invention.
  • Fig. 36 illustrates a femoral-popliteal bypass procedure, in accordance with a preferred embodiment of the invention.
  • Performing an anastomosis connection with a coronary vessel may be a first or a second step of performing a bypass between an aorta and the vessel or it may be a single anastomosis step in a longer process, for example when connecting a LIMA or a RIMA to a coronary using a side-to-end anastomosis connection.
  • this anastomosis connection is problematic for example for one or more of the following reasons:
  • the coronary vessels and especially diseased ones have a very weak structure and are difficult to handle and stretch.
  • the tools used for performing the anastomosis are all outside the graft and the coronary.
  • anastomotic connector be long ( in an axial dimension), as a minimal intra-body profile is desired.
  • Figs. 1A-1D schematically illustrate two parts of a two part anastomotic device 100 of a preferred embodiment of the present invention, in isometric-perspective and in cut- through views.
  • Figs. 1 A and IB illustrate a ring portion 102, preferably formed of a tubular element 104.
  • a plurality of apertures 110 are formed in the tubular element.
  • the tubular element may be formed of a mesh or another construction that is naturally open.
  • the total amount of foreign material in the body is preferably reduced.
  • tubular element 104 can radially expand or contract, for example plastically, elastically, super-elastically or using shape-memory.
  • Another possibly advantage of using a mesh element is that the anastomosis device is more flexible and can accommodate variations in tissue geometry and can even deform over time, for example if the vessels enlarge.
  • a plurality of flange elements 108 are preferably provided around the circumference of tubular element 104.
  • each of these flange elements has an aperture defined in it and are used to hold a spike element (described below).
  • these flange elements function as a flange over which a blood vessel is everted and/or otherwise attached to.
  • the flange elements of the tubular element include barbs to engage an everted blood vessel.
  • the flange elements serve to stiffen the tube element so that it does not collapse radially.
  • the graft is engaged by tubular element 104.
  • the engagement is by contact, in others, a mechanical coupling is provided, for example, friction, using barbs on element 104, using glue, or as a result of eversion over the flange.
  • a plurality of locking elements 106 are preferably provided on tubular element 104, for example on an opposite side from the flange elements, to lock the spike elements in place when anastomosis device 100 is deployed.
  • the locking elements are elongate, so that their length provides some elasticity with respect to the locking. Thus, some relative elastic motion of the spikes and the tubular element is possible even after locking.
  • other types of axial motion allowing mechanisms may be provided, for example making the spikes axially elastic (with respect to the forces expected in the anastomosis connection).
  • An elastic locking device is preferably achieved by providing or placing the locking elements distal from the flange of tubular element 104.
  • the locking elements may be near the flange or even on the flange. Additionally, the locking elements can be at or near the flange for other reasons, for example, if no elastic motion is desired.
  • Figs. 1C and ID illustrate a spike-portion 120, preferably formed of a ring 122 having a plurality of spikes 124 attached thereto.
  • the diameter of the ring is slightly greater than that of tubular element 104. It is noted however, that in some preferred embodiments of the invention one or both of ring portion 102 and spike portion 120 are radially expandable.
  • spike portion 120 is radially expandable.
  • flange elements 120 is mounted on ring portion 102 by inserting each of spikes 124 through a flange element 108 while sliding ring 122 over tube element 104.
  • flange elements In some implementations, flange elements
  • the spikes are pushed through the apertures of closed flange elements.
  • the spikes may be slid in through an opening.
  • the openings are on the sides of the flange elements and spike portion 120 is mounted onto ring portion 102 by rotating the spike portion 120 so that the spikes enter the flange elements through the openings.
  • Ring 122 is preferably relatively rigid. However, in some embodiments, where ring
  • ring 122 is not required to maintain its shape, but mainly assist in retracting spikes 124, the ring may be made more flexible. It should be noted that ring 122 may be open, however, it is preferably a closed ring. Preferably, locking elements 106 (Figs. 1A, IB) operate by engaging ring 122, once it is retracted over them.
  • ring 122 is sine-shaped, with the spikes connected to parts of the sine distal from the flange.
  • the ring relaxes, it retracts the spikes.
  • Spikes 124 may be of many different designs. However, in a preferred embodiment of the invention, the spikes are curved inwards towards their ends and have a bent end 126, with a sharp tip 128. In some embodiments, especially as described below, spikes 124 may include a twist.
  • the curve of the spikes is preferably super-elastic, in that the spikes are pre-formed to be bend and are maintained in a straightened configuration during at least part of the deployment process. However, elastic, plastic, shape memory and other mechanical types of bending may also be practiced in preferred embodiments of the invention.
  • Figs. 2A-2F schematically illustrate the operation of anastomosis device 100, shown in a side cross-sectional view.
  • Fig. 2 A shows anastomosis device 100 after it is mounted on a graft 130, such that a spike 124 transfixes a partially everted portion 134 of the graft (e.g., everted less than 180°).
  • the spikes are curved in, such that when ring 122 is retracted, as shown in Fig. 2B, the spikes are straightened by the ring portion 102, preferably by flange elements 108. After they are straightened or during the straightening process a target vessel 132 is preferably transfixed by tips 128 of the spikes.
  • the spike tips transfix vessel 132 even before the spikes are unbent.
  • the spikes flare out as well, for example to widen the opening and/or to otherwise geometrically mold the connection between the blood vessels.
  • the effect of strengthening the spikes is achieved, in some embodiments by relative motion of the two connector parts. In some embodiments, this motion includes retraction of the spikes relative to vessel 132. Alternatively, the spikes are maintained in a fixed position in space relative to vessel 132 or even advanced.
  • Fig. 2C illustrates an alternative to Fig. 2A, in which the spikes are not bent inwards.
  • An opening 136 in the target vessel may be widened during the insertion of the spikes or the spikes may be bent inwards, for example by an enclosing tube.
  • Other methods of bending the spikes may also be used, for example, using torsion forces, or by temperature treating shape- memory formed spikes.
  • bent end 126 may be sharp enough to transfix the target vessel when the spikes are advanced.
  • tip 128 is compressed against spike 124, so bent end 126 has a smaller profile.
  • vessel 132 is perfused, for example using blood, saline solution, possibly through its lumen and possibly through opening 136, so that the walls of vessel 132 are separated.
  • ring 122 is retracted sufficiently, locking elements 106 preferably engage the ring and/or the spikes, locking them in place.
  • Fig. 2D shows a final state in which spike tips 128 contact or lock against the bottom of the flange elements or into the flange elements.
  • Fig. 2E shows a final state in which spike tips 128 contact or lock against the side of flange elements.
  • spike tips 128 neither contact nor lock against the flange elements. It is noted that by controlling the configuration of the anastomosis device and the eversion, spike tips 128 can be made to pierce or to not pierce everted portion 134 of graft 130. Although tips 128 may transfix even everted portion 134, in a preferred embodiment of the invention, tips 128 are not exposed, to prevent them catching on other, nearby, tissue and damaging it. Thus, in some embodiments of the invention, including those described elsewhere herein, when a vessel is transfixed, the piercing of the vessel may be through or it may be part way.
  • Fig. 3 A is a plan layout of ring portion 102, in accordance with a preferred embodiment of the invention.
  • Fig. 3B is a plan layout of spike portion 120, in accordance with a preferred embodiment of the invention. A plurality of optional openings 129 are shown in ring 122.
  • FIGs. 4A-4D illustrate a method of retracting a ring portion of the anastomosis device of Figs. 1A-1D, in accordance with a preferred embodiment of the invention.
  • a schematically shown insertion tool 140 preferably includes a ring retractor 142 having a ring engaging portion 144. Ring engaging portion 144 may be designed to engage openings 129.
  • ring engaging portion 144 may engage ring 122 from its underside.
  • engager 144 comprises a plurality of fingers which when retracted away from vessel 132, pull ring 122 along with them. An advantage of these fingers engages openings 129, is that they provide a method of advancing the ring 122.
  • ring retractor 142 When ring retractor 142 is retracted, for example as shown in Fig. 4B, ring 122 and spikes 124 are also retracted. When the retraction is sufficient ring 122 is engaged by a locking element 106.
  • an extension 148 of insertion tool 140 prevents engagement of the locking elements until the extension is retracted, allowing correction of errors.
  • locking element 106 when it engages ring 122, disengages the engager 144, for example by pushing the engaging fingers away radially. Alternatively, engager 144 may compress locking elements 106, thereby preventing their operation.
  • Removing the device may include pushing in locking elements 106 and/or advancing the spikes so that they bend inwards. Possibly, it is required to grip vessel 132, so that the spikes retract from it.
  • Fig. 4C in a preferred embodiment of the invention, when retractor 142 is pull beck further, engager 144 is bent out of the way by a protrusion (or thickening) 146 of tool 140.
  • Fig. 4D shows the completed anastomosis after insertion tool 140 is removed.
  • spike 124 typically, but not necessarily, digs into the side vessel, thereby having less exposed surface to the blood flow.
  • tool 140 does not surround the graft vessel from all sides, for example enclosing only 270° thereof.
  • a slot is defined in the side of tool 140, through which the tool can be removed from the graft, once the anastomosis is completed.
  • the locking action of locking elements 106 against ring 122 is slightly flexible, to allow some adaptation to variations in local anatomy and especially to avoid applying too much pressure on the blood vessel portions compressed by the anastomosis device.
  • the flexibility is set to match a desired range of pressures, for example, not so low that blood will leak and not so high as to cause tissue necrosis. Alternatively or additionally, this flexibility allows adaptation to variations in blood vessel thickness among blood vessels, among patients and/or in a single blood vessel.
  • This flexibility may be provided in many ways, for example, by one or more of making locking elements 106 flexible, by making tubular element 104 flexible, by making spikes 124 axially flexible and/or by making bent area 126 of the spikes flexible.
  • the spikes include a spring portion, for example an S curve at their base, which spring portion can vary in length to modify the distance of the spike tip from a locking element or ring 122.
  • spikes 124 and especially the bending area 126 burrow into the "side" blood vessel 132, so that there is practically no contact between the spikes and the blood flow.
  • the pressure on the spike is preferably regulated, for example as described above, to prevent necrosis.
  • Tubular element 104 serves as a collar when anastomosis device 100 is deployed.
  • the length of this collar may be a factor in the suitability of the anastomosis device.
  • the collar is made as short as possible. alternatively, excess material may be cut off, for example after the anastomosis device is deployed.
  • an oblique connector (as described below) can have a generally lower profile relative to the blood vessel.
  • tubular element 104 is formed of two rings separated by a spring. Once the anastomosis is completed, the element is released and the collar contacts. Optionally, the contraction of the collar provides the locking function of elements 106, by engaging a portion of the spike between the two rings.
  • Other structures which axially contract for example a sine-shape, may also be used.
  • Fig. 5 is a plan layout of a one piece anastomosis device 200, in accordance with a preferred embodiment of the invention.
  • a numbering scheme similar to that of Figs. 3 A and 3B has been used to illustrate the similarity between the anastomosis devices.
  • An advantage of a one piece anastomosis device is the reduction or elimination of a need to control the relative orientation of two pieces. Alternatively or additionally, as there is only one piece, it is easier to grasp and is less likely to get lost in the patient's body. Also, as only one piece is provided, locking flanges may be dispensed with and spring action may be provided by dedicated springs 223 and 225.
  • springs 225 are used for the main retraction of the spikes, and springs 223 provide some flexibility with respect to the exact amount of retraction.
  • a spike 224 is advanced by pressing on its associated stud 227. When the stud is released, the springs retract the spike.
  • the spike is forcefully retracted by engaging it at point 229, where the spike has a thickening.
  • at least one of the two springs 225 and 223 is plastically deformed, rather than elastically deformed.
  • a stop is provided to prevent the spikes from extending too far once they were retracted.
  • Figs. 6A and 6B are side cut-through images of an anastomosis area, showing a method of performing an anastomosis using anastomosis device 200. As can be seen from the figures, the process is very similar to that of Figs. 4A-4F, except that anastomosis device 200 is composed of only one piece and no locking is performed.
  • flange 208 is shown bent back up in a portion 209. This bending is optional, however, it may, for example, strengthen the anastomosis connection, protect the tips 228 of the spikes from causing damage to nearby body structures and/or allow pinching of vascular tissue by forcing the tissue with the spikes into the aperture of flange 208.
  • a degree of elasticity with respect to the relative positions of the spikes is preferably allowed, as described above.
  • the freedom allowed is between 0J and 2 mm, for example about 0.5 mm or about 1.5 mm.
  • the amount of freedom typically depends on the parameters of the anastomosis connections, including the pressures, the blood vessel geometries and the number of spikes used to make the connection.
  • ANASTOMOSIS DEVICE VARIATIONS Fig. 7A is a schematic illustration of a split spike tip configuration 260, in accordance with a preferred embodiment of the invention.
  • This spike configuration is preferably used for an aortic type anastomotic connector, for example as described in PCT/IL99/00284, the disclosure of which is incorporated herein by reference. However, this type of spike configuration may be used for other anastomotic connectors.
  • configuration 260 is used for holding the pierced blood vessel together, for example to prevent dissection, and not for exerting pressure either towards or away from the anastomotic connector, alternatively, the spike may also exert such radial pressure.
  • a spike 252 splits into two tines 254.
  • the tines are long enough to penetrate into the aorta (or other "side") vessel, but do not transfix it. Alternatively, they do transfix it.
  • Thickening 253 or the crotch of the split serves as a stop which prevents penetration of the spike to far into the aorta.
  • the thickening is also used as an anchor point for manipulating the anastomosis device during deployment.
  • the tines vary in width and/or thickness, to resist retraction of the tines. Such geometric variations may also be provided on the spikes.
  • Fig. 7B is a side cut-through view of a connector including configuration 250, deployed in an aorta 256, in accordance with a preferred embodiment of the invention. As shown, tines 254 hold together two aorta layers 258 and 260 (third, intermediate layer) is not shown.
  • a benefit of a fork shaped spike end is in assisting locking between the spikes on opposite sides of the anastomosis connection.
  • needle-eye shaped tips, enclosing an aperture, rather than open tines may be used.
  • the tines (or spike itself) are barbed, to prevent retraction of the spike.
  • the spike is barbed along its length, to provide a ratchet mechanism, in which the spike can only advance one way. This can provide a self-tightening anastomotic connection, especially in conjunction with springs, as described above, that allow some relative motion between the spike and the anastomotic connector.
  • the spike cross-section is preferably that of a smoothed corner rectangle.
  • the cross-section may be triangular (e.g., facing away or towards the bend in the spike), circular oval or rectangular (e.g., with thick or thin side to the bend).
  • the cross-section of the spike is not aligned with the bend direction.
  • the cross-section may change over the length of the spike. This can be achieved, for example by chemical etching, laser cutting, cold working or twisting of the spike.
  • An advantage of some of these spike cross-sectional configuration is that the provide maximum strength in a desired direction, while providing flexibility in other directions.
  • the cross-section may better dig into the blood vessel and away from the blood flow.
  • some spike shapes are expected to cause less damage to at least some layers of the blood vessel, while being inserted.
  • Fig. 8A is a plan layout of an aortic anastomotic connector in accordance with a preferred embodiment of the invention.
  • Fig. 8B is a top view of the connector of Fig. 8A, in a resting state.
  • Fig. 8C is an enlargement showing the meeting of two spikes from opposing sides of the connector.
  • Fig. 8D is a view through line A- A of Fig. 8B, showing the relative placement of the spikes from two sides of the anastomosis device, in a resting state. Exemplary measurements are provided on the figures, but they should not be considered limiting on the connector for other embodiments.
  • the connector is preferably made of Nitinol, and is trained to the resting position shown using the molds of Figs. 9A and 9B.
  • a tube is laser cut as shown in Fig. 8A (or a plate is cut and then welded into a tube after being shaped on a mandrel) to form the connector.
  • the tubular connector is preferably mounted on a mandrel 262, preferably an expandable mandrel that engages the connector snugly.
  • the spikes of the connector are bent around a ring mold 264 and surrounded by a two part external mold having parts 266 and 268.
  • the molded connector is then placed into an oven to be heat treated and then preferably quenched, for example in water.
  • the external mold is removed and ring mold 264 is also removed, for example by bending back the spikes.
  • only a single heat-treatment is used for training the entire connector.
  • the diameter of the metal used for the spikes is between 0.07 and 0J mm, similar to the diameter of thread commonly used for bypass suturing.
  • Tubular element 104 may be thicker, for example, 0J mm, however this is not essential.
  • the connector is formed of Nitinol, however, other materials may be used, for example stainless steel or a polymer, such as a plastic or a composite material. Possibly, a bio-degradable plastic is used.
  • the connector may be formed of two or more different materials, for example, each section ot a different material or even a same section of two or more materials.
  • the connector is formed at least in part from allograft or xenograft materials.
  • ring 122 may be formed of sinew.
  • the graft is preferably an allograft, for example a mammary artery or a peripheral vein.
  • the connector is mounted on the graft outside the body, possibly in a remote location.
  • FIG. 10 is a flowchart of an exemplary process 300 of keyhole bypass, in accordance with a preferred embodiment of the invention.
  • the graft may be provided through a hole in the chest, through a blood vessel or be harvested in the chest region.
  • the connections may be performed endoscopicly, transvascularly or using open surgery.
  • one of the connections may be eliminated, for example if a mammary artery is used.
  • Another type of variation is the time at which the graft is prepared for connection (e.g., when the connector is attached). This preparation can be done inside the body, or in a different country, in a two extreme examples.
  • the time line of the process is also flexible, depending on the types of materials and techniques used.
  • Process 300 is described as a generalized process, although account should be taken of the possible variations.
  • the by pass procedure is started (302). This usually involves opening one or more keyholes in the chest and/or other openings in the body.
  • the heart may or may not be stopped and the vessel to be bypassed to may or may not be blocked.
  • a graft is provided (304).
  • the graft may be harvested from the patient (e.g., a leg vein) or provided from a package. This may be done before or after the procedure proper has started.
  • the graft is a semi-connected or a disconnected mammary artery, which may be harvested and/or prepared through the keyholes.
  • a connector e.g., 100 or 200
  • the vessel may be everted (306), before, during or after mounting the anastomotic connector.
  • Steps 310-316 describe one such connection.
  • a hole is punched in the target blood vessel.
  • the puncner is lert in the hole to prevent blood leakage from the punched hole.
  • the graft with the connector is then inserted in the hole (312).
  • the connector is partially deformed or allowed to deform into a partially deploy situation, before or after it is inserted.
  • connection is then made (314), preferably by completing the deforming of the device, but in some embodiments, by pulling or pushing the device.
  • the tool is then removed (316). In some embodiments, the tool surrounds the graft.
  • the toll may be removed from the other end of the graft.
  • the tool is dismantled.
  • the tool is split apart.
  • the tool is cut away from the blood vessel.
  • the tool does not surround the graft from all sides, while it is in use.
  • steps 304, 306 and/or 308 are repeated as well.
  • a step of Quality Assurance (QA) 318 is preferably performed, in which the connections are inspected for leaks and/or to assure that the connectors are properly deployed.
  • An exemplary check can be to see if all the spikes are properly deployed and pierce the vessels they are supposed to.
  • the testing may be, for example, visual or radiographic.
  • EXEMPLARY TOOL SET Fig. 11 is a schematic illustration of a scaffold tool 400, which holds various other tools during a bypass procedure, in accordance with a preferred embodiment of the invention.
  • Tool 400 preferably includes a handle 402 and a shaft 401 extending from the handle.
  • a particular feature of this embodiment is a slot 404 extending along substantially the entire scaffold 400, which allows substantially free entry and exit of a graft vessel, although, as described below, it is sufficient for the slot to be present at the distal tip of the tool.
  • a tip 408 of the tool is preferably formed so that it can fit inside a hole punched in a blood vessel during the anastomosis connection.
  • An area 406, at the end of tool 400 preferably has high sides (e.g., it has a nearly complete circumference, except for a graft removal slot), to aid in maintaining the configuration of tools inserted inside scaffold 400, as will be explained below.
  • area 406 serves as a stop which prevents unlimited insertion of tool 400 into a blood vessel.
  • An area 410 has lower sides than area 406, to allow such inserted tools to split apart and free an enclosed graft as described below. Other configurations can also be used.
  • Tip 408 is preferably mounted on an extension which is separate from scaffold 400, and is retracted from it when it is time to remove the tools from the graft or during the deployment of the anastomosis connector. However, tip 408 is preferably present starting before the hold punching operation (at which point it is pushed into the punched hole) until after some or all the other tools are removed and the anastomosis completed.
  • Scaffolding tool 400 preferably includes alignment slots (not shown), to properly align tools inserted into it.
  • Tip 408 is preferably made of plastic, however, it may be made of metal.
  • the rest of tool 400 is preferably formed of rigid plastic, as known in the art.
  • Tool 400 may be disposable. Alternatively, it may be sterilized and reused, for example using sterilization methods known in the art.
  • tools which are inserted into scaffold 400 are mechanically split apart when they are retracted, if they enclose the graft. Thus, the graft can be removed from the tool. Alternatively or additionally, to mechanical splitting, the tools may be cut with a knife, possible one which forms a part of scaffold 400 or of the inserted tool.
  • the inserted tool is preferably pre-formed with a slit (or two) to facilitate removal.
  • most of the tool is open, for example formed like a bar, with only a ring at the tip to enclose the blood vessel.
  • the tool may be damaged by the removal process so that it can only be used once. Alternatively, it is only plastically or elastically deformed, so that it can be bent back into shape, sterilized and reused.
  • HOLE PUNCHERS When punching a hole in a blood vessel, several issues arise, some or all of which are preferably addressed by preferred embodiments of the invention:
  • a punching operation consists generally of two steps: (i) making a puncture in the target vessel using a tool; and
  • the motion of the punching tool, for step (i) and/or for step (ii) is achieved without axial motion of tool 400.
  • a first type of punching element is shown in Figs. 12A-12D, as a hole puncher 420.
  • hole puncher 420 may be designed for use with a scaffold tool 400, or for use as a stand-alone tool.
  • after the hole is punched tool 400 is brought (typically forcefully) over a portion of the punch which remains in the punched hole to prevent leakage and/or to guide in tip 408.
  • Hole puncher 420 comprises a tube 423 which splits into two (or more) flaring out tongues 424. Alternatively, the entire tube may be split. A sleeve 426 is provided so that when tube 423 is retracted, the tongues are brought together. In Fig. 12A, a portion of a vessel 422 is engaged by the tongues, by pressing against the vessel.
  • Fig. 12B the tube is retracted a small amount and the tongues grasp a portion 428 of vessel 422.
  • tongues 424 have a cutting edge formed on their inner surface, mounted on a perpendicular section.
  • tube 423 is further retracted, thereby cutting out portion 428.
  • Fig. 12D The resulting vessel 422 with a punched hole is shown in Fig. 12D.
  • this hole puncher by suitably setting the aperture defined by tongues 424, the puncher can avoid engaging both sides of the blood vessel at a same time.
  • a separate cutter (not shown) may be used to cut the engaged portion 428.
  • Figs. 13A-13D illustrate a process of using a rotating spike hole punch 430, in accordance with a preferred embodiment of the invention.
  • Punch 430 preferably comprises an inner grasping element 432, preferably a vacuum tube and an external cutting element 434, preferably including at least one spike 436.
  • Fig. 13B is a perspective view of external cutting element 434.
  • grasping element 432 is brought in contact with vessel 422 and engages it, for example using vacuum or using an internal grasper (not shown).
  • grasping element 432 is slightly retracted, to avoid inadvertently damaging the other side of vessel 422 while the hole is formed.
  • cutting element 434 is advanced towards vessel 422, so that spike 436 penetrates it.
  • spike 436 cuts a round hole in vessel 422.
  • Spike 436 is preferably straight and is slightly longer or the same length as the wall of vessel 422 is thick.
  • spike 436 is sickle shaped and is inserted into vessel 422 using a rotational motion.
  • FIG. 13D shows vessel 422 with the resulting punched hole.
  • ANVIL PUNCH Figs. 14A-14E illustrate a process of using an anvil hole puncher 440, in accordance with a preferred embodiment of the invention.
  • a sharp edge 442 is used to form a slit 444 in vessel 422.
  • anvil hole puncher 440 comprises an inner element 446 having an anvil 452 formed at its end and an outer element 448 having cutting edges 450 formed at its end. Alternatively or additionally, the cutting edges and the anvil may trade places or only cutting edges may be used.
  • Anvil 452 is inserted into vessel 422 through hole 444. Then, as shown in Fig. 14D, the anvil is retracted until vessel 422 is cut between anvil 452 and cutters 450.
  • Fig. 14E shows the resulting punched hole.
  • an enclosing tube (not shown, but could be tip 408) is preferably inserted into the punched hole.
  • the enclosing tube preferably has a valve through which the punch is inserted and when the punch is removed, the valve seals and no blood leaks out.
  • the enclosing tube may be pushed into the hole.
  • the tube may be screwed into the hole, for example by defining a thread on the tube's outside.
  • blood loss may be avoiding by perfusing vessel 422 with saline solution instead of or in addition to allowing blood flow.
  • This preferably serves a purpose of preventing vessel 422 from collapsing, if it is weak or serves a purpose of clearing away blood.
  • Such saline flow may also be provided through the hole puncher itself.
  • An additional advantage of perfusing vessel 422 is that the side that is being worked on (punching, device connection) is thus distanced from the other side of the vessel, reducing the probability of damage to the other side of the vessel.
  • Figs. 15A-15D illustrate a hole puncher 460 designed to be inserted in scaffold tool 400, in accordance with a preferred embodiment of the invention
  • puncher 460 comprises a shaft 462 having at a distal end thereof a handle 464, for operating the punch and at the other end, a sharp tip 466 for piercing the blood vessel to be punched.
  • the shaft defines a narrowing 468, into which the pierced blood vessel is guided, for example by pushing tip 466 forward, or by a back-angle (not shown) on tip 466.
  • Distal of narrowing 468 is an anvil 470.
  • anvil 470 has an external angle, to assist in moving the punched blood vessel form the punch to tip 408 (of scaffold 400).
  • Fig. 15C shows punch 460 inserted in a scaffold 400.
  • Fig. 15D is an enlargement of the proximal end of punch 460, inserted in scaffold 400, when the punch is operated.
  • a fixed diameter area 467 is provided between anvil 470 and tip 466, to prevent the punched blood vessel from slipping off the punch.
  • An incline is preferably provided in anvil 470, to assist in advancing the punched vessel onto tip 408 of scaffold 400.
  • FIGs. 16A and 16B illustrate in perspective view and in cut-open view, respectively, a tip-retracting hole punch 480, in accordance with a preferred embodiment of the invention.
  • Punch 480 comprises a sharp retracting tip 486, an anvil 490, a narrowing 488 defined between tip 486 and anvil 490, and a cylindrical portion 487 between tip 486 and narrowing
  • the punching action is caused by retracting tip 486, preferably using a shaft or cable 492 into a hollow 494 formed in cylindrical portion 487.
  • tip 486 is further retracted, cylinder 487 is pulled back against anvil 490, cutting the blood vessel in narrowing 488 between them using a ridge 496 defined on cylinder 487 and/or anvil 490.
  • scaffold 400 and/or tip 408 include a seal, for example an iris or leaflet seal, through which the punch can be inserted and retracted, while preventing leakage of blood as long as tip 408 is in the punched hole.
  • a seal for example an iris or leaflet seal
  • Fig. 17 is a cut-open view of a tip retracting hole punch 500, in accordance with an alternative preferred embodiment of the invention.
  • the retracting of a tip 506 by a shaft 502 does not pull back a cylindrical portion 507 to cut vessel 422 against a cutting edge 512 of an anvil 510.
  • the motion of tip 506 and of portion 507 may be separate and independent. Alternatively, the two motions may be caused by a single control.
  • a peg or other means at the distal end of shaft 502 couples the motion of shaft 502 to the motion of cylinder 507 and/or anvil 510.
  • FIG. 18 is a showing of an assembled and a taken apart oblique hole puncher 520, which can be used to make holes having a lumen that is not perpendicular to a blood vessel, in accordance with a preferred embodiment of the invention.
  • the form of the hole may be circular, elliptical or other shaped, even polygonal, depending on the shape of the punch elements.
  • Puncher 520 comprises generally of an outer tube 528 having a forward cutting edge, an inner element 524, a retracting tip 522 that fits inside inner element 524 and can be retracted, for example as described above, and a cutting piece 526, which is retracted by inner element 524 against the forward cutting edge, to punch a hole in vessel 422.
  • the location of the cutting edges and the anvils can be varied in other embodiments. Additionally, retracting tip 522 is optional.
  • the plane defined by cutting piece 526 is not parallel to the forward cutting edge, although it may be made parallel. Rather, an angular difference of between 5° and 15° and preferably about 5° is provided. For example, for a 45° punch, the forward cutting edge is 45° (on the back of inner element 524) and cutting piece 526 has an angle of 50°.
  • the separation of cutting piece 526 from inner element 524 may allow lower cost machining of the cutting edge and puncturing tip. Alternatively or additionally, by replacing cutting edge 526, different angles of punching can be achieved.
  • Fig. 19A is a schematic illustration of an alternative oblique hole puncher 530 in accordance with another preferred embodiment of the invention.
  • Puncher 530 utilizes a solid tip element 532 having a forward tip 536 and a back cutting face 538.
  • a matching (optionally non-parallel) forward cutting face 534 is provided to cut vessel 422 between them.
  • Fig. 19B is a showing of tip element 532, in two views.
  • the embodiment shown here includes a plurality of groves 542 formed in the tip. These groves are not essential, however, they appear to reduce the need to rotate the tip while puncturing the blood vessel.
  • An opening 540 for a pin to attach the tip to a shaft is also preferably provided.
  • Back cutting face 538 preferably includes an inclined portion 544 and a relatively flat portion 546, to assist in holding the blood vessel.
  • rotation of the tip of the puncher is provided by vibrating the tip and/or the rest of the puncher.
  • the rotation may be provided manually.
  • the device is on the outside of the graft and the graft has an intima-to-intima connection with the blood vessel.
  • most of the device is outside the graft and the anastomosis connection.
  • the graft is everted over the connector, such that the spikes extend from the graft and the rest of the connector is under or distal the everted portion of the graft.
  • the eversion may be partial (e.g., about 90°) or complete (e.g., about 180°). However, other degrees of eversion can also be utilized.
  • the eversion process itself is usually not easy, since the graft is slippery and small and resists manipulation. An additional problem is that the spikes may be hooked and not suitable for insertion through a graft without causing great damage.
  • Figs. 20A-20D illustrates a transfixing-based eversion method (b), in accordance with a preferred embodiment of the invention.
  • a benefit of the particular embodiment shown in Figs. 20A-20D is that the eversion device is nearly completely outside the graft, so that one end of the graft may already be connected to the patient.
  • a graft 551 is inserted inside a vessel holder 552.
  • a connector 554 having a plurality of forward spikes 556 is mounted on a connector holder 564.
  • One or more tip maintainers 562 are preferably provided to keep spikes 556 of connector 554 from bending back to their relaxed position (e.g., in super elastic or elastic devices).
  • the end of graft 551 is engaged by a plurality of lips 560, which are coupled to an expander 558.
  • expander 558 is expanded, thereby increasing its radius and causing lips
  • Fig. 20C connector 564 is advanced, thereby causing spikes 556 to transfix the end of graft 551.
  • Fig. 20D the end result is shown, in which a partial eversion is achieved. It is noted that spikes 556, once released from tip maintainers 562, bend. Optionally, lips 560 prevent bending of spikes 556 back into graft 551. The various expanders and tip holders may now be removed.
  • the spikes are inserted at an angle to the wall of the graft, thereby providing a partial inversion of the graft and/or maintaining the graft in the configuration caused by the spreading apart of the graft end.
  • Figs. 21A-21E illustrate a graft everter 570, in accordance with a preferred embodiment of the invention.
  • Graft 551 is inserted in a graft holder 564 (possibly having mounted thereon an anastomosis connector) and only its tip protrudes.
  • Holder 564 may be held in one hand and everter 570 in another hand. Alternatively, one or both may be bench mounted and/or coupled to each other.
  • Connector 554 (not shown) may be mounted on holder 564.
  • Everter 570 comprises a main body 571, including a switch 580 and a head 572.
  • a detail of head 572 is shown in Fig. 21B.
  • a tip 574 preferably rounded, is provided such that the end of graft 551 can be mounted on it.
  • An expander 579 having a plurality of fingers 578 is used to expand the graft tip, as described below.
  • a plurality of stop-fingers 576 is preferably provided to control the advance of graft 551 over tip 574 and fingers 578.
  • the relative location of stop-fingers 576 and tip 574 can be controlled, for example to control the amount of eversion or to allow a more stable hold on the graft.
  • Fig. 21C is a detail of expander 579.
  • Fig. 21D is a side section through expander 579 showing graft 551 mounted on it.
  • a pin 582 is advanced, causing expander 579 to expand.
  • the vessel is everted by advancing graft holder 564 with graft 551, so that it is inside fingers 578.
  • the advancing the graft 551 includes advancing of the anastomosis connector, thereby transfixing the graft.
  • the extent of advancing may be controlled, if required, for example, by the resistance of the graft or by stop-fingers 576.
  • pin 582 When pin 582 is retracted, fingers 578 move inward and the eversion is complete.
  • pin 582 also advances the tube enclosing expander 579.
  • This tube also serves as a stop to further expansion of fingers 578, trapping the graft between the fingers and the tube.
  • stop-fingers 579 include small spikes at their tips and are also expanded by pin 582, thus engaging the graft from the inside.
  • pin 582 A further advance of pin 582 causes the stop-fingers (now everting fingers) to evert the graft off of fingers 578. This motion mimics the manual process of everting using a forceps, except that the graft is only engaged from the inside. Alternatively, the graft is engaged both from inside and from outside. ALTERNATIVE TWO PART GRAFT EVERTER
  • Fig. 22 is a schematic cut-through illustration of an alternative graft everter 590, in accordance with a preferred embodiment of the invention.
  • the graft is engaged by the everter, additionally or alternatively to engaging only the graft tip (as in the embodiment of Figs. 21A-21E).
  • An expanding tip 594 preferably mounted at the end of a body 592, preferably grasps graft 551 from the inside. Graft 551 may or may not be mounted inside a graft holder 564.
  • tip 594 is an expanding silicone tip, which is expanded by a pressure source 596.
  • An exemplary pressure source comprises a rod, which when pressed into a silicon tip 594, it causes it to deform. Alternatively, other expanding or grasping mechanisms may be used.
  • a plurality of fingers (or a complete ring) 598 is provided, with an engaging edge 591.
  • engaging edge 591 pushes the rim of graft 551 back, thereby everting the graft.
  • the eversion may be by a single advance of the fingers. Alternatively, each such advance rolls the graft back an additional small amount.
  • the spikes of the connector which transfix the everted vessel are in a bent state during the transfixing.
  • the spikes are bent after the transfixing.
  • shape memory materials such as those that bend when heated, may be used.
  • the heating may be for example, in ambient air of a room or by passing an electric current through the connector.
  • the tip of the spike is shape memory, so that the rest of the spike is rigid enough to be inserted through the graft.
  • a shield for example a tube with one fmger for each spike, is provided over the connector while it is advanced, to maintain the spike tips in a straight configuration.
  • the spikes may be bent after they transfix, for example by plastic deformation. Possibly the spike is heat-treated at the bend point, after transfixing the graft, to "learn" the new configuration.
  • FIGs. 23A-23G illustrate a method of transfixing a blood vessel by twisting spikes of a connector, in accordance with a preferred embodiment of the invention.
  • Fig. 23A shows a connector 600 that can be similar to the connector of Figs. 2, except that spikes 602 (only one shown) are bent so that tips 604 (only one shown) point in, rather than out.
  • Connector 600 preferably comprises a spike section 601 and a tubular section 603.
  • a sleeve 608 is preferably provided to protect an inserted graft 551 (Fig. 23B) from accidentally transfixing on tip 604.
  • the resting configuration of tips 604 is out and they are twisted in and maintained in this position by a twist maintainer 606.
  • this is not essential.
  • spikes 602 may be plastically twisted after graft 551 is transfixed. It should be noted that plastic deformation is possible also in super elastic devices, for example by over-rotation.
  • graft 551 is inserted into the graft holder, under sleeve 608.
  • sleeve 608 is removed, allowing contact between graft 551 and tips 604.
  • graft 551 is transfixed by tips 604.
  • graft 551 is pulled forward out of the graft holder and/or stretched, for example using a device such as shown in Figs. 21.
  • connector 600 is retracted, possibly while inflating a balloon or other expandable element inside graft 551, to prevent its motion and/or control the transfixing.
  • an optional step of advancing the spike relative to the everted portion of graft 551 is shown. This step may also be performed later, or may be omitted.
  • twist maintainer 606 is removed (or the spikes twisted) so that the spikes twist and tips 604 point out.
  • Fig. 23 G shows the completed transfixing process, after an optional step of retracting the graft over the spikes.
  • rotation of spikes to achieve an easier transfixing and/or eversion may also be practiced in staple embodiments, where the anastomosis is performed using a plurality of individual staples, each of which can be rotated around its long axis, similarly to the twist of spike 602 as shown.
  • SIMULATED EVERSION Mammary arteries in general, are relatively thick and difficult to evert. Applicants have discovered, surprisingly, that the mammary artery can be manipulated to have an effective everted area, without actually everting the artery and while applying a relatively low amount of stress to the artery.
  • Figs. 24A-24D illustrate a method of simulating an eversion, especially for a mammary artery, in accordance with a preferred embodiment of the invention.
  • Fig. 24A shows one wall of a mammary artery 620. It is noted that other types of blood vessels and graft materials may be used instead.
  • Fig. 24B an internal mold 622 and a vessel engaging external framework 621 are provided, to engage artery 620.
  • the engaging means may be any known in the art, for example a friction surface or small barbs.
  • framework 621 is advanced so that the end of artery 220 is pushed against a shaping portion 623 of mold 622 and widens.
  • shape portion 623 and external framework 621 By suitable selection of the geometry of mold 622, shaping portion 623 and external framework 621, the size and type of distortion can be controlled.
  • framework 621 and/or mold 622 are ridged, to cause a ripple in artery 620.
  • a perpendicular mold is shown, an oblique mold or a mold that otherwise shapes the end of artery 620, for example into a saddle shape, may be used.
  • the thickened part of artery 620 is transfixed by a spike 228 of a connector 626, for example using methods described herein.
  • Mold 622 may include apertures so that it does not damage spike 228.
  • a LIMA is compressed as much as 1 cm.
  • a connector 632 for example an aortic connector transfixes a thickened portion 630 of artery 620.
  • a ring portion 634 is outside the thickening.
  • a blood vessel or graft is shaped by compressing it to have thickenings (not only at its end) and inserting one or more spikes or a connector through the thickening, to maintain the shaping effect. INSERTING THE CONNECTOR Once the graft is everted and transfixed by the connector, the connector and graft are to be attached to target vessel 422, in the punched hole. Once the connection is completed, the tools must be removed from the graft.
  • Fig. 25A is a cut-through close-up of scaffold tool 400 when a combination graft holder and connector holder 640 is inserted therein, showing graft 551 schematically, but not showing a connector.
  • Fig. 25B is a perspective view of Fig. 25A.
  • Holder 640 preferably comprises two layers, an inner layer 642, which preferably holds a connector (not shown) on its surface and an outer layer 644 which assists in inserting the device into the aorta (or other target vessel) and protects the everted part of graft 551. Alternatively or additionally, layer 644 maintains the straight configuration of the spikes.
  • the everted part of graft 551 is preferably between layer 644 and tip 408, however, it may also be between layers 642 and 644.
  • Layer 642 preferably includes protrusions to grasp the connector by thickening on it
  • Fig. 7 For example, the tines of the spikes of Fig. 7 can be located in an area 650 of the layer, while the body of the connector is in an area 640 of the layer. A ring of protrusion 646 prevent motion of the connector.
  • a similar configuration can be used to hold a two part device, such as described in Fig. 2.
  • layer 642 may include notches at its tips to allow the bent spikes to be bent inwards.
  • a knife blade 654 is preferably provided to rip apart layer 644, as described below in more detail. In operation, either tip 408 is retracted or layers 642 and 644 advanced, so that the target vessel is in contact with an area 652 on the outside of layer 644.
  • Layer 644 is retracted, such that the forward spikes of the connector can bend.
  • FIG. 26 shows the situation after tip 408 is retracted, showing spikes 124 that engage target vessel 422.
  • the relative movement of the various layers and tubes is provided by a mechanism in the handle of the tool, preferably operated by a simple control, such as knob 653.
  • the connector may be mounted between layers 642 and 644, for example, by placing the relaxed graft on layer 642 and then bending back the back spikes so that they can be covered with layer 644.
  • the bending back may be, for example using a forceps or using a dedicated tool.
  • the connector is cooled, for example using liquid
  • the connector may be mounted in the following manner.
  • a notched over tube is brought over the mandrel, so that the notch engages one of the back spikes of the connector.
  • the notched tube is rotated, causing the engaged spike to be captured between the over tube and the mandrel, in a substantially straight configuration.
  • Step (c) is repeated for all the spikes.
  • tip 408 and layer 644 are retracted, they are preferably slit by knife 654 of layer
  • the layers may be pre-split and removed using a peg or cone which splits tip 408 and/or layer 644.
  • Fig. 27 shows only layer 642, emphasizing a pre-formed slit in the layer, knife 654 and protrusions 646.
  • Fig. 28 is a cut-through view of tools 400 and 640, showing a peg or a cone 656 which splits apart layer 642 when layer 642 is retracted sufficiently.
  • peg or a cone 656 which splits apart layer 642 when layer 642 is retracted sufficiently.
  • peg or a cone 656 which splits apart layer 642 when layer 642 is retracted sufficiently.
  • 656 may be closer to the tip of scaffold 400 and/or it may be movable into position, when required.
  • Figs. 29A-29F illustrate an alternative connector delivery system 700 having an outside
  • Fig. 29B is a cut-through view showing a magazine 705, a connector holder 706 and a splitting pin 708 attached to a rod 707.
  • pin 708 splits apart the layers it is in contact with, for example holder 706 and magazine 705.
  • a retracting knife may be used.
  • Fig. 29C shows only magazine 705 with a connector 709 poking out at its tip.
  • a hollow 715 and a slit 716 for peg 708 to operate are shown as well.
  • Fig. 29D shows an over-tube 704, used to seal the hole in the target vessel after the hole is punched in it. Again, a slot and a slit for peg 708 to operate are shown. Outside 703 preferably engages over-tube 704 snugly enough to prevent blood leakage through the slit.
  • the slit area may comprise clot enhancing material.
  • the slit area may be coated with a flexible material, such as rubber.
  • Fig. 29E illustrates device holder 706 and device 709, illustrating a slit and a slot in holder 706 and illustrating an protrusion based connector engaging element 718.
  • Fig. 29F is a cut-through view of the handle area of system 100, showing a mechanism for retracting portions of the system by squeezing a pair of handles 702. The squeezing is transmitted by a lever 714 to a pair of sliders 717. When sliders 717 are retracted enough, they retract holder 706 and magazine 705, via a pair of coupling pins 710. This retraction causes the forward spikes of device 709 to engage the target blood vessel, once the target blood vessel is engaged, only magazine 705 continues its retraction. As magazine 705 retracts, device 709 is freed and engages the target vessel using its backward spikes
  • OBLIQUE ANASTOMOSIS CONNECTOR Figs. 30A-30D which correspond to Figs. 1A-1D illustrate an anastomosis connector
  • the element numbers correspond to those of figs. 1 A-1D, except that they are all "800" numbers rather than "100" numbers.
  • Using an oblique connector allows connections geometries which can be more useful than a perpendicular geometry, for example to accommodate the angle of arrival of a graft, to accommodate nearby structures and/or for better blood flow.
  • the connection may be oblique with respect to the axis of the target vessel or its transaxial direction. Exemplary oblique angles include, between 10° and 80°, more preferably between 30° and 70° and in an exemplary embodiment, about 45°.
  • Fig. 31 A which corresponds to Fig. 2F shows connector 800 during deployment.
  • Fig. 3 IB which corresponds to Fig. 2D, shows a completed oblique anastomosis.
  • Figs. 32A and 32B which correspond to Figs. 3A and 3B show a layout view of connector 800 of Figs 30A-30D.
  • the actual device may be shorter than the device shown, for example having only five spikes.
  • a generally tubular connector is shown, oval geometries or other geometries are provided in other preferred embodiments of the invention.
  • Everting an oblique graft is generally more difficult than everting a regular graft. Generally, one side of the graft, at the wider angle of the connector, is more easily everted, while the graft portion at the narrow angle, is less easily everted.
  • FIGs. 33A and 33B illustrate a variation in the eversion devices to assist in this difficulty.
  • a device 800 on a graft 551 has a tip 839 at the narrow angle side of the graft.
  • a holder 840 which is provided to hold connector 800, preferably also bends tip 839 inward using a protrusion 842, so that it can more easily transfix graft 551, using any of the techniques described above.
  • protrusion 842 is bend out of shape, for example by connector 800 when holder 840 is retracted.
  • Figs. 34A-34F illustrate a self-everting connector 850 and a method of deploying such a connector, in accordance with a preferred embodiment of the invention.
  • Fig. 34A shows one segment of connector 850, including a body section 858, a back spike 854, a forward spike 856 and a manipulation tab 858.
  • connector 850 is inserted into a vessel 422 and is mounted on a graft 551, such that forward spikes 856 are rotated into the graft lumen.
  • This unnatural (in a super-elastic, elastic or shape-memory connector) position is preferably maintained by a tab holder 862 that presses against tabs 858.
  • plastic deformation methods are used.
  • Spikes 854 are preferably curved in to assist insertion into vessel 422, however this is not required.
  • An over tube 860 is preferably provided outside of holder 862.
  • over tube 860 is preferably advanced, to push vessel 422 away from the device and allow space for the eversion.
  • the eversion may also be performed deeper into vessel 422 if space allows.
  • holder 862 is retracted, releasing tabs 858 and allowing spikes 856 to twist back to their relaxed position, thereby everting graft 551.
  • Retraction of device 850 transfixes vessel 422 using spikes 856. Then, over tube 860 is retracted further, freeing spikes 864 to engage vessel 422 from the other side. As shown in the
  • retraction of over tube 860 may be impeded by spikes 854.
  • a small amount of space is provided between over tube 860 and holder 862 to allow for spike 854.
  • axial slots may be defined in over tube 860, allowing spikes 854 to be released by axially rotating over tube 860 relative to connector 850.
  • Fig. 34F shows a completed anastomosis.
  • aorto-femoral bypass or other bypasses of vessels that provide blood to the lower limbs may be performed in other parts of the body, such as the head, the brain, the abdomen or the extremities, for example, to perform an aorto-femoral bypass or other bypasses of vessels that provide blood to the lower limbs.
  • the above described anastomotic connectors can be modified for the other locations. Preferably approximately one spike per mm perimeter is provided. Thus, a femoral device may have seven spikes.
  • a kit is provided, including a graft.
  • the connectors are pre-mounted on the graft, at one or both ends (possibly more if the graft has additional openings or splits). Fig.
  • the connector is embedded in the wall of the graft, for example during its manufacture or by inserting the device after the graft is completed.
  • at least part of the graft overlaying the connector is adapted to bond well to a blood vessel to which it will be attached.
  • the very end of the graft may optionally be manufactured to not cause coagulation if it is in contact with blood. The more distal portions may be manufactured to enhance coagulation.
  • an end-connector is shown, a similar embedding may be performed for a side-type connector.
  • a kit for performing a bypass procedure includes a graft and a guide wire or other guide for guiding the graft between the anastomosis locations.
  • FIG. 36 illustrates an exemplary femoral-popliteal bypass procedure, in accordance with a preferred embodiment of the invention.
  • a bypass using graft 870 is to be performed between a point 886 on a superficial femoral artery 876 and a point 888 on a popliteal artery 878.
  • keyhole openings 882 and 884 are made over points 886 and 888.
  • Device 874 on one end of graft 870 is attached at point 886, for example as described above.
  • a guide wire 880 is used to pull graft 870 through the body to the area of keyhole 884.
  • guide wire 880 is rigid or includes a rigid guide member to more easily navigate between the two keyholes.
  • Guide wire 880 is preferably attached to graft 880 using a suture.
  • the anastomosis and navigation between the two points is performed endoscopicly, or transvascularly (at least providing the graft).
  • the above method sand device scan be adapted for use in many kinds of surgery, for example endoscopic, transvascular keyhole and open surgery.
  • the manipulation of blood vessels and grafts may be performed completely inside the body, for example everting a LIMA through a keyhole.
  • the above described methods of vascular surgery may be varied in many ways, including, changing the order of steps, which steps are performed inside the body and which outside, the order of making the anastomosis connections, the order of steps inside each anastomosis, the exact materials used for the anastomotic connectors and/or which vessel is a "side" side and which vessel (or graft) is an "end" side of an end-to-side anastomosis.
  • the location of various elements may be switched, without exceeding the sprit of the disclosure, for example, switching the anvil for the cutting edge in the hole-punching devices and switching the moving elements for non-moving elements where relative motion is required.
  • surgical kits which include sets of medical devices suitable for making a single or a small number of anastomosis connections.
  • Section headers are provided only to assist in navigating the application and should not be construed as necessarily limiting the contents described in a certain section, to that section. Measurements are provided to serve only as exemplary measurements for particular cases, the exact measurements applied will vary depending on the application.
  • the terms "comprises”, “comprising”, “includes”, “including” or the like means “including but not limited to”. It will be appreciated by a person skilled in the art that the present invention is not limited by what has thus far been described. Rather, the scope of the present invention is limited only by the following claims.

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Abstract

L'invention concerne un raccord d'anastomose destiné à relier une greffe à un vaisseau cible, et comprenant une section mince du type collier (104) conçue pour s'emboîter sur une portion de la greffe, ainsi qu'une section garnie de pointes (124), conçue pour s'emboîter sur la section du type collier et comprenant plusieurs pointes (126), chaque pointe (126) étant conçue pour transpercer la greffe. De préférence, ce raccord comprend au moins un élément de blocage destiné à bloquer la section garnie de pointes (124) et la section de collier (104), et exerçant une action ressort entre les deux sections.
PCT/IL1999/000670 1998-05-29 1999-12-08 Chirurgie vasculaire WO2000056226A1 (fr)

Priority Applications (46)

Application Number Priority Date Filing Date Title
JP2000606135A JP2002538925A (ja) 1999-03-19 1999-12-08 血管手術法
US09/936,806 US7063711B1 (en) 1998-05-29 1999-12-08 Vascular surgery
AU15831/00A AU768923B2 (en) 1999-03-19 1999-12-08 Vascular surgery
KR1020017011929A KR20020067616A (ko) 1999-03-19 1999-12-08 혈관 수술
IL14546099A IL145460A0 (en) 1999-03-19 1999-12-08 Vascular surgery
EP99958467A EP1171042A1 (fr) 1999-03-19 1999-12-08 Chirurgie vasculaire
BR9917217-8A BR9917217A (pt) 1999-03-19 1999-12-08 Conector, aparelho para distribuir um enxerto para uma anastomose, processos de remover uma ferramenta de distribuição de enxerto de um enxerto encerrado, de conter e liberar um conector anastomótico, de realizar uma anastomose, de everter um enxerto, de montar um conector de anastomose, de simular eversão de um enxerto, de transfixar um conector em um enxerto e de tratar termicamente um conector de anastomose, mecanismo de punção para puncionar um furo em um vaso sanguìneo, conjunto para um procedimento de contorno, punção e eversor de enxerto
MXPA01009475A MXPA01009475A (es) 1999-03-19 1999-12-08 Cirugia vascular.
NZ514744A NZ514744A (en) 1999-03-19 1999-12-08 Vascular surgery
CA002366703A CA2366703A1 (fr) 1999-03-19 1999-12-08 Chirurgie vasculaire
AU15835/00A AU1583500A (en) 1999-03-19 1999-12-09 Vascular closure device
US09/936,789 US7060084B1 (en) 1998-05-29 1999-12-09 Vascular closure device
BR0009172-3A BR0009172A (pt) 1999-03-19 1999-12-09 Conector para anastomose, processa para fazer aeversão de um vaso sanguìneo, aparelho paraeversão de enxerto de um enxerto sobre um eixoque tem uma ponta, processo para medir umadimensão de enxerto, punção de furo, processopara formar um conector para anastomoseoblìqua, e, sistema de distribuição montado delado
PCT/IL1999/000674 WO2000056223A1 (fr) 1999-03-19 1999-12-09 Dispositif d'obturation vasculaire
BR0016251-5A BR0016251A (pt) 1999-12-08 1999-12-09 Dispositivo de ligação vascular para vedar uma abertura entre dois rebordos de condutos sanguìneos, e, método para vedar uma abertura entre dois rebordos de condutos sanguìneos.
AU33136/00A AU3313600A (en) 1999-03-19 2000-03-20 Advanced closure device
US09/936,805 US6979338B1 (en) 1998-05-29 2000-03-20 Low profile anastomosis connector
IL14543100A IL145431A0 (en) 1999-03-19 2000-03-20 Low profile anastomosis connector
CA002366708A CA2366708A1 (fr) 1999-03-19 2000-03-20 Raccord d'anastomose bas profil
EP00911144A EP1171044A1 (fr) 1999-03-19 2000-03-20 Raccord d'anastomose bas profil
NZ514745A NZ514745A (en) 1999-03-19 2000-03-20 Low profile anastomosis connector
CN00805205A CN1353594A (zh) 1999-03-19 2000-03-20 小轮廓吻合连接器
MXPA01009472A MXPA01009472A (es) 1999-03-19 2000-03-20 Conector de anastomosis de perfil bajo.
AU33138/00A AU769269B2 (en) 1999-03-19 2000-03-20 Low profile anastomosis connector
KR1020017011866A KR20010113767A (ko) 1999-03-19 2000-03-20 낮은 프로파일의 문합 커넥터
JP2000606137A JP2002538926A (ja) 1999-03-19 2000-03-20 ロー・プロファイル・コネクタ
US09/936,796 US6726704B1 (en) 1998-05-29 2000-03-20 Advanced closure device
PCT/IB2000/000302 WO2000056227A1 (fr) 1999-03-19 2000-03-20 Dispositif de fermeture perfectionne
BR0016247-7A BR0016247A (en) 1999-12-08 2000-09-28 Anastomotic devices and methods
PCT/IL2000/000609 WO2001041623A2 (fr) 1999-05-30 2000-09-28 Dispositifs et procedes d'anastomose
CA002393508A CA2393508A1 (fr) 1999-12-08 2000-09-28 Dispositifs et procedes d'anastomose
JP2001542802A JP2003515416A (ja) 1999-12-08 2000-09-28 吻合装置および方法
EP00964605A EP1259169A2 (fr) 1999-12-08 2000-09-28 Attache des levres d'un vaisseau sanguin
EP00964603A EP1237485A2 (fr) 1999-12-08 2000-09-28 Dispositifs et procedes d'anastomose
PCT/IL2000/000611 WO2001041624A2 (fr) 1999-05-30 2000-09-28 Attache des levres d'un vaisseau sanguin
AU75525/00A AU7552500A (en) 1999-12-08 2000-09-28 Anastomotic devices and methods
IL15000300A IL150003A0 (en) 1999-12-08 2000-09-28 Anastomotic devices and methods
IL15005100A IL150051A0 (en) 1999-05-30 2000-09-28 Blood vessel lip attachment
AU75527/00A AU7552700A (en) 1999-12-08 2000-09-28 Vessel lip attachment
CA002393486A CA2393486A1 (fr) 1999-12-08 2000-09-28 Attache des levres d'un vaisseau sanguin
JP2001542803A JP2004513670A (ja) 1999-12-08 2000-09-28 血管縁部結合器
HK02103911.8A HK1042030A1 (zh) 1999-03-19 2002-05-25 薄型吻合連接器
US10/459,407 US20040073247A1 (en) 1998-05-29 2003-06-11 Method and apparatus for forming apertures in blood vessels
US10/668,059 US20050101983A1 (en) 1998-05-29 2003-09-22 Method and apparatus for forming apertures in blood vessels
AU2004201487A AU2004201487A1 (en) 1999-03-19 2004-04-07 Vascular surgery
US11/210,554 US20050283188A1 (en) 1998-05-29 2005-08-23 Vascular closure device

Applications Claiming Priority (6)

Application Number Priority Date Filing Date Title
IL12906799A IL129067A0 (en) 1998-05-29 1999-03-19 Methods and devices for vascular surgery
IL129067 1999-03-19
ILPCT/IL99/00284 1999-05-30
PCT/IL1999/000285 WO1999062408A1 (fr) 1998-05-29 1999-05-30 Dispositif de fermeture de perforations dans le systeme vasculaire
PCT/IL1999/000284 WO1999062415A1 (fr) 1998-05-29 1999-05-30 Techniques et dispositifs de chirurgie vasculaire
ILPCT/IL99/00285 1999-05-30

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PCT/IL1999/000284 Continuation-In-Part WO1999062415A1 (fr) 1998-05-29 1999-05-30 Techniques et dispositifs de chirurgie vasculaire
US09701531 Continuation-In-Part 1999-05-30
US09936805 Continuation-In-Part 2000-03-20

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PCT/IL1999/000284 Continuation-In-Part WO1999062415A1 (fr) 1998-05-29 1999-05-30 Techniques et dispositifs de chirurgie vasculaire
US09701531 Continuation-In-Part 1999-05-30
US09936806 A-371-Of-International 1999-12-08
US09/936,806 A-371-Of-International US7063711B1 (en) 1998-05-29 1999-12-08 Vascular surgery
US09/936,789 Continuation-In-Part US7060084B1 (en) 1998-05-29 1999-12-09 Vascular closure device
PCT/IL1999/000674 Continuation-In-Part WO2000056223A1 (fr) 1998-05-29 1999-12-09 Dispositif d'obturation vasculaire
US09936789 Continuation-In-Part 1999-12-09
US10/459,407 Continuation-In-Part US20040073247A1 (en) 1998-05-29 2003-06-11 Method and apparatus for forming apertures in blood vessels
US10/459,373 Continuation-In-Part US20040049221A1 (en) 1998-05-29 2003-06-11 Method and apparatus for forming apertures in blood vessels
US10/668,059 Continuation-In-Part US20050101983A1 (en) 1998-05-29 2003-09-22 Method and apparatus for forming apertures in blood vessels
US10/809,274 Continuation-In-Part US20050038454A1 (en) 1998-05-29 2004-03-25 Anastomotic delivery system

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JP (2) JP2002538925A (fr)
KR (2) KR20020067616A (fr)
CN (2) CN1352539A (fr)
AU (5) AU768923B2 (fr)
BR (2) BR9917217A (fr)
CA (2) CA2366703A1 (fr)
HK (1) HK1042030A1 (fr)
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US10631864B2 (en) 2014-08-12 2020-04-28 Anastomosis As Minimally traumatic anastomosis

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BR9917217A (pt) 2002-02-26
EP1171042A1 (fr) 2002-01-16
WO2000056223A1 (fr) 2000-09-28
AU769269B2 (en) 2004-01-22
AU2004201487A1 (en) 2004-05-06
CA2366703A1 (fr) 2000-09-28
CN1353594A (zh) 2002-06-12
AU768923B2 (en) 2004-01-08
HK1042030A1 (zh) 2002-08-02
NZ514744A (en) 2004-01-30
AU3313800A (en) 2000-10-09
AU1583500A (en) 2000-10-09
CA2366708A1 (fr) 2000-09-28
KR20020067616A (ko) 2002-08-23
MXPA01009475A (es) 2004-03-19
KR20010113767A (ko) 2001-12-28
AU3313600A (en) 2000-10-09
MXPA01009472A (es) 2003-08-19
AU1583100A (en) 2000-10-09
EP1171044A1 (fr) 2002-01-16
JP2002538926A (ja) 2002-11-19
JP2002538925A (ja) 2002-11-19
NZ514745A (en) 2003-08-29
CN1352539A (zh) 2002-06-05
BR0009172A (pt) 2001-12-18

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