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US20010016700A1 - Transmyocardial implant with flow reduction - Google Patents

Transmyocardial implant with flow reduction Download PDF

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Publication number
US20010016700A1
US20010016700A1 US09/304,730 US30473099A US2001016700A1 US 20010016700 A1 US20010016700 A1 US 20010016700A1 US 30473099 A US30473099 A US 30473099A US 2001016700 A1 US2001016700 A1 US 2001016700A1
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Prior art keywords
conduit
wall
blood flow
vessel
heart wall
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US09/304,730
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US6409697B2 (en
Inventor
Robert A. Eno
Guy P. Vanney
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Horizon Technology Funding Co LLC
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HeartStent Corp
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Publication date
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Priority to US09/304,730 priority Critical patent/US6409697B2/en
Assigned to HEARTSTENT CORPORATION reassignment HEARTSTENT CORPORATION ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: ENO, ROBERT A., VANNEY, GUY P.
Publication of US20010016700A1 publication Critical patent/US20010016700A1/en
Priority to US10/155,926 priority patent/US6916304B2/en
Application granted granted Critical
Publication of US6409697B2 publication Critical patent/US6409697B2/en
Assigned to PERCARDIA, INC. reassignment PERCARDIA, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: HEARTSTENT CORPORATION
Assigned to HORIZON TECHNOLOGY FUNDING COMPANY LLC reassignment HORIZON TECHNOLOGY FUNDING COMPANY LLC ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: PERCARDIA, INC.
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/94—Stents retaining their form, i.e. not being deformable, after placement in the predetermined place
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
    • A61F2/2493—Transmyocardial revascularisation [TMR] devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/00234—Surgical instruments, devices or methods for minimally invasive surgery
    • A61B2017/00238—Type of minimally invasive operation
    • A61B2017/00243—Type of minimally invasive operation cardiac
    • A61B2017/00247—Making holes in the wall of the heart, e.g. laser Myocardial revascularization
    • A61B2017/00252—Making holes in the wall of the heart, e.g. laser Myocardial revascularization for by-pass connections, i.e. connections from heart chamber to blood vessel or from blood vessel to blood vessel
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
    • A61F2220/0075—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements sutured, ligatured or stitched, retained or tied with a rope, string, thread, wire or cable

Definitions

  • This invention pertains to an implant for passing blood flow directly between a chamber of the heart and a coronary vessel. More particularly, this invention pertains to such an implant with an enhance design for reducing a likelihood of damage to a coronary vessel from a high -velocity blood flow discharge.
  • Implants such as those shown in the aforementioned patent and applications include a portion to be placed within a coronary vessel and a portion to be placed within the myocardium.
  • the vessel When placing a portion of the implant in the coronary vessel, the vessel is incised a length sufficient to insert the implant.
  • the implant When placed within the coronary vessel, the implant discharges flow axially into the vessel.
  • a portion of an interior surface of the implant portion in the vessel acts as a deflection surface to prevent direct impingement of high velocity blood flow on a vessel wall.
  • the L-shaped implant described in the foregoing is preferably placed through a surgical procedure (open chest or minimally invasively).
  • the suitability of an implant for minimally invasive or percutaneous procedures is influenced, at least in part, by the external size and shape of the implant.
  • the size can be reduced and shape enhanced by elimination of the vessel portion of the foregoing designs.
  • a transmyocardial implant for establishing a blood flow path through a heart wall between a heart chamber and a lumen of a coronary vessel on the heart wall.
  • the implant includes a hollow conduit having an open first end and an open second end.
  • the conduit is dimensioned so as to extend at least from the vessel through said heart wall and into said chamber.
  • the conduit has a conduit wall defining a blood flow pathway within an interior of said conduit between the first and second ends.
  • the first and second ends are mutually positioned for the first end to reside within the vessel and opposing a wall of the vessel when the conduit is placed within the heart wall with the second end protruding into the chamber.
  • the conduit wall is formed of a material sufficiently rigid to resist deformation and closure of the pathway in response to contraction of the heart wall.
  • a flow restriction is formed in the pathway for reducing a discharge velocity of blood flow discharged from the first end.
  • FIG. 1 is a schematic cross-sectional view of an implant according to the present invention in place in a heart wall to define a blood flow path from a left ventricle to a coronary artery distal to an obstruction.
  • an implant 10 including a straight elongate, generally cylindrical tube or conduit 11 .
  • the conduit 11 may be formed of titanium or other rigid biocompatible material such as pyrolytic carbon or may be titanium coated with pyrolytic carbon.
  • the interior wall 13 of the conduit 11 is polished to a high degree of polish to reduce the likelihood of thrombus formation on the wall.
  • the material of the conduit 11 is preferably a rigid material in order to withstand contraction forces of the heart wall, as will be described.
  • the tube 11 will have an outside diameter Do of about 1 to 3 millimeters and an internal diameter D1 of about 0.5 to 2.5 millimeters to provide a wall thickness of about 0.5 millimeters.
  • a specific D o may be 2.5 millimeters and a specific D1 may be 2.0 millimeters.
  • the tube 11 has a first open end 12 which is sized to be received within the lumen of a coronary vessel such as the lumen 100 of a coronary artery 102 illustrated in FIG. 1.
  • a coronary vessel such as the lumen 100 of a coronary artery 102 illustrated in FIG. 1.
  • the term “vessel” refers to veins or arteries.
  • the present invention is described with reference to bypassing a coronary artery with blood from a left ventricle. The invention is equally applicable to forming a blood flow path from other heart chamber to any other coronary vessel.
  • the conduit 11 has a second open end 14 .
  • the conduit 11 is sized to extend from the coronary artery 102 directly through the heart wall 104 and protrude into the left ventricle 106 of a patient's heart.
  • the end 14 protrudes at least about 5 millimeters from an inner surface 103 of the heart wall 104 during maximum heart wall thickness during systole.
  • Heart wall thickness varies from patient to patient and among locations on the heart.
  • the length L of the conduit (measured as the axial distance between ends 12 and 14 ) will be between about 10 and 30 millimeters. With the foregoing specific example, for a heart wall 104 having a maximum systolic thickness of 20 millimeters, the length L of the conduit 11 is 25 millimeters.
  • the openings 12 , 14 communicate with an interior 20 of the conduit 11 . Therefore, blood can freely flow through the conduit 11 between the left ventricle 106 and the lumen 100 of the coronary artery 102 .
  • the conduit 11 is outwardly flared at 22 to act as a stop to limit insertion of the implant 10 into the heart wall 104 . Further, the flaring 22 acts as a smooth flow path for guiding blood flow out of end 12 .
  • the tube 11 is preferably formed of titanium or other smooth biocompatible material in order to resist thrombus formation on the inner surface 13 of the conduit 11 .
  • Titanium is a presently preferred material due its long-term use in the cardiovascular industry. Further, titanium is sufficiently rigid to withstand deformation forces caused by contraction of the heart wall 104 to avoid deformation of the tube 11 so that the tube 11 remains open during both diastole and systole. Also, the tube 11 is solid on its cylindrical inner surface 13 . Therefore, highly thrombogenic material from the heart wall 104 cannot pass into and contaminate the interior 20 of the conduit 11 .
  • a completed implant 10 includes a sleeve 24 of tissue growth-inducing material secured to an exterior surface of the conduit 11 .
  • the sleeve 24 is attached to the conduit 11 by a suture 23 tightly surrounding both the sleeve 24 and conduit 11 .
  • the sleeve 24 surrounds the exterior surface of the tube 11 and is recessed back from both of ends 12 , 14 so that after placement the sleeve 24 resides solely in the heart wall 104 (although slight protrusion of sleeve 24 into the left ventricle can be tolerated). It is desired the sleeve not be so closely positioned near open ends 12 , 14 such that tissue growth on the sleeve 24 can grow over and occlude the open ends 12 , 14 . It is anticipated that tissue growth on and into the sleeve 24 could result in a buildup of tissue beyond the sleeve 24 to a thickness of about at least 1 millimeter. It is desirable that such tissue growth does not extend over ends 12 , 14 . Accordingly, the sleeve 24 is spaced from ends of the tube 11 by a distance greater than an anticipated thickness of tissue growth extension beyond the sleeve 24 .
  • the sleeve 24 is selected to induce tissue growth and attachment.
  • the sleeve 24 is formed of a fabric having biocompatible fibers defining interstitial spaces to receive tissue growth.
  • a fabric is polyethylene terephthalate (such as polyester fabric sold by DuPont Company under the trademark Dacron).
  • polyethylene terephthalate such as polyester fabric sold by DuPont Company under the trademark Dacron.
  • Such a fabric permits rapid tissue integration into the fabric thereby anchoring the fabric and, hence, the tube 11 to the patient's tissue.
  • the tissue growth inducing material could be sintered metal on the external surface of the tube 11 .
  • Sintered metal results in a porous surface to receive tissue growth.
  • the area of the sintered metal will be spaced from ends 12 , 14 to prevent tissue accumulation on the sintered area from growing over and blocking 12 , 14 .
  • the exterior surface of the tube 11 can be roughened.
  • the roughening can be in the form of a knurling or other roughened surface due to sandblasting or the application of sinter beads. The roughening results in surface protrusions and pitting, around which tissue may grow.
  • the implant 10 is placed with the first end 12 placed within the artery lumen 100 distal to an obstruction 105 .
  • Normal nourishing blood flow is in the direction of arrow A.
  • the implant 10 passes through the heart wall 104 with the second end 14 positioned within the left ventricle 106 and spaced from the inner surface 103 of the heart wall 104 by 5 millimeters during periods of maximum heart wall thickness.
  • the sleeve 24 is positioned opposing the heart wall 104 so that tissue from the heart wall 104 can grow into the sleeve 24 .
  • the first opening 12 opposes a wall 102 a of the artery 102 .
  • blood discharged from the opening 12 impinges directly upon the arterial wall 102 a .
  • the artery wall 102 a is a fragile layer of cells and fibers. Direct impingement of blood flow on the wall 102 a can damage the artery wall 102 a . As a healing response to such damage, a cellular matrix may develop and proliferate to such an extent that opening 12 or lumen 100 could occlude.
  • the present invention reduces the velocity of blood flow through the opening 12 .
  • a flow restriction in the form of a narrowing 30 is placed within the conduit 11 .
  • the restriction 30 reduces blood flow below a velocity which would otherwise cause occluding trauma to the artery wall 102 a.
  • the restriction 30 results in a narrow interior diameter D of about 0 . 5 millimeters.
  • the narrow restriction 30 is positioned about 8 millimeters from end 14 .
  • the restriction 30 is formed by a venturi constriction formed within the conduit 11 adjacent end 14 .
  • the venturi may be formed by machining the conduit 11 from a solid blank of titanium.
  • the venturi 30 has a shallow ramp 31 on a downstream side to avoid turbulence. Since an upstream side 33 is adjacent end 14 , turbulence during reverse flow is not a serious concern.
  • the blood flow velocity from end 12 is reduced to a velocity of normal blood flow within an artery 102 (about 30 ml/min.). Since the left ventricle 106 has a high maximum pressure, the pressure differential between the ventricle 106 and artery lumen 100 results in a higher than normal blood flow rate in the absence of the restriction 30 .
  • the tube 11 is a cylinder with circular cross-section.
  • the tube 11 could have an oval cross-section at end 12 to provide a larger flow area and further reduce flow velocity.
  • the tube 11 is preferably straight, the tube 11 could be bent so that the direction of blood flow from end 12 is not perpendicular to the arterial blood flow direction A.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Cardiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Transplantation (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Prostheses (AREA)

Abstract

A transmyocardial implant establishes a blood flow path through a heart wall between a heart chamber and a lumen of a coronary vessel on the heart wall. The implant includes a hollow conduit having an open first end and an open second end. The conduit is dimensioned so as to extend at least from the vessel through said heart wall and into said chamber. The conduit has a conduit wall defining a blood flow pathway within an interior of said conduit between the first and second ends. The first and second ends are mutually positioned for the first end to reside within the vessel and opposing a wall of the vessel when the conduit is placed within the heart wall with the second end protruding into the chamber. The conduit wall is formed of a material sufficiently rigid to resist deformation and closure of the pathway in response to contraction of the heart wall. A flow restriction is formed in the pathway for reducing a discharge velocity of blood flow discharged from the first end.

Description

    BACKGROUND OF THE INVENTION
  • 1. Field of the Invention [0001]
  • This invention pertains to an implant for passing blood flow directly between a chamber of the heart and a coronary vessel. More particularly, this invention pertains to such an implant with an enhance design for reducing a likelihood of damage to a coronary vessel from a high -velocity blood flow discharge. [0002]
  • 2. Description of the Prior Art [0003]
  • Commonly assigned U.S. Pat. No. 5,755,682 and PCT International Publication No. WO 98/06356 teach an implant for defining a blood flow conduit directly from a chamber of the heart to a lumen of a coronary vessel. An embodiment disclosed in the aforementioned patent and application teaches an L-shaped implant. The implant is a conduit having one leg sized to be received within a lumen of a coronary artery and a second leg sized to pass through the myocardium and extend into the left ventricle of the heart. As disclosed in the above-referenced patent and application, the conduit remains open for blood flow to pass through the conduit during both systole and diastole. The conduit penetrates into the left ventricle in order to prevent tissue growth and occlusions over an opening of the conduit. [0004]
  • Commonly assigned and co-pending U.S. patent application Ser. No. 08/944,313 filed Oct. 6, 1997, entitled “Transmyocardial Implant”, and filed in the name of inventors Katherine S. Tweden, Guy P. Vanney and Thomas L. Odland, teaches an implant such as that shown in the aforementioned '682 patent with an enhanced fixation structure. The enhanced fixation structure includes a fabric surrounding at least a portion of the conduit to facilitate tissue growth on the exterior of the implant. [0005]
  • Implants such as those shown in the aforementioned patent and applications include a portion to be placed within a coronary vessel and a portion to be placed within the myocardium. When placing a portion of the implant in the coronary vessel, the vessel is incised a length sufficient to insert the implant. When placed within the coronary vessel, the implant discharges flow axially into the vessel. A portion of an interior surface of the implant portion in the vessel acts as a deflection surface to prevent direct impingement of high velocity blood flow on a vessel wall. [0006]
  • The L-shaped implant described in the foregoing is preferably placed through a surgical procedure (open chest or minimally invasively). The suitability of an implant for minimally invasive or percutaneous procedures is influenced, at least in part, by the external size and shape of the implant. The size can be reduced and shape enhanced by elimination of the vessel portion of the foregoing designs. [0007]
    • SUMMARY OF THE INVENTION
  • According to a preferred embodiment of the present invention, a transmyocardial implant is disclosed for establishing a blood flow path through a heart wall between a heart chamber and a lumen of a coronary vessel on the heart wall. The implant includes a hollow conduit having an open first end and an open second end. The conduit is dimensioned so as to extend at least from the vessel through said heart wall and into said chamber. The conduit has a conduit wall defining a blood flow pathway within an interior of said conduit between the first and second ends. The first and second ends are mutually positioned for the first end to reside within the vessel and opposing a wall of the vessel when the conduit is placed within the heart wall with the second end protruding into the chamber. The conduit wall is formed of a material sufficiently rigid to resist deformation and closure of the pathway in response to contraction of the heart wall. A flow restriction is formed in the pathway for reducing a discharge velocity of blood flow discharged from the first end. [0008]
    • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1 is a schematic cross-sectional view of an implant according to the present invention in place in a heart wall to define a blood flow path from a left ventricle to a coronary artery distal to an obstruction. [0009]
    • DESCRIPTION OF THE PREFERRED EMBODIMENT
  • With reference to FIG. 1, an implant [0010] 10 is shown including a straight elongate, generally cylindrical tube or conduit 11. The conduit 11 may be formed of titanium or other rigid biocompatible material such as pyrolytic carbon or may be titanium coated with pyrolytic carbon. Preferably, the interior wall 13 of the conduit 11 is polished to a high degree of polish to reduce the likelihood of thrombus formation on the wall. The material of the conduit 11 is preferably a rigid material in order to withstand contraction forces of the heart wall, as will be described.
  • In the preferred embodiment, the tube [0011] 11 will have an outside diameter Do of about 1 to 3 millimeters and an internal diameter D1 of about 0.5 to 2.5 millimeters to provide a wall thickness of about 0.5 millimeters. By way of non-limiting example, a specific Do may be 2.5 millimeters and a specific D1 may be 2.0 millimeters.
  • The size range given permits insertion of the conduit into a coronary vessel to be bypassed. Commonly, such vessels in an adult human have internal diameters of 1 to 3 millimeters when under the influence of normal pressurized blood flow. [0012]
  • The tube [0013] 11 has a first open end 12 which is sized to be received within the lumen of a coronary vessel such as the lumen 100 of a coronary artery 102 illustrated in FIG. 1. As used in this application, the term “vessel” refers to veins or arteries. The present invention is described with reference to bypassing a coronary artery with blood from a left ventricle. The invention is equally applicable to forming a blood flow path from other heart chamber to any other coronary vessel.
  • The conduit [0014] 11 has a second open end 14. The conduit 11 is sized to extend from the coronary artery 102 directly through the heart wall 104 and protrude into the left ventricle 106 of a patient's heart. Preferably, the end 14 protrudes at least about 5 millimeters from an inner surface 103 of the heart wall 104 during maximum heart wall thickness during systole. Heart wall thickness varies from patient to patient and among locations on the heart. In a preferred embodiment of forming a flow path from the left ventricle to a coronary artery of an adult human, the length L of the conduit (measured as the axial distance between ends 12 and 14) will be between about 10 and 30 millimeters. With the foregoing specific example, for a heart wall 104 having a maximum systolic thickness of 20 millimeters, the length L of the conduit 11 is 25 millimeters.
  • The [0015] openings 12, 14 communicate with an interior 20 of the conduit 11. Therefore, blood can freely flow through the conduit 11 between the left ventricle 106 and the lumen 100 of the coronary artery 102.
  • At [0016] first opening 12, the conduit 11 is outwardly flared at 22 to act as a stop to limit insertion of the implant 10 into the heart wall 104. Further, the flaring 22 acts as a smooth flow path for guiding blood flow out of end 12.
  • As mentioned, the tube [0017] 11 is preferably formed of titanium or other smooth biocompatible material in order to resist thrombus formation on the inner surface 13 of the conduit 11. Titanium is a presently preferred material due its long-term use in the cardiovascular industry. Further, titanium is sufficiently rigid to withstand deformation forces caused by contraction of the heart wall 104 to avoid deformation of the tube 11 so that the tube 11 remains open during both diastole and systole. Also, the tube 11 is solid on its cylindrical inner surface 13. Therefore, highly thrombogenic material from the heart wall 104 cannot pass into and contaminate the interior 20 of the conduit 11.
  • While tissue will adhere to titanium, the adhesion may be inadequate when subjected to the shearing contracting forces of the [0018] heart wall 104 due to the relative smoothness of extruded titanium. Therefore, a completed implant 10 includes a sleeve 24 of tissue growth-inducing material secured to an exterior surface of the conduit 11. The sleeve 24 is attached to the conduit 11 by a suture 23 tightly surrounding both the sleeve 24 and conduit 11.
  • The [0019] sleeve 24 surrounds the exterior surface of the tube 11 and is recessed back from both of ends 12, 14 so that after placement the sleeve 24 resides solely in the heart wall 104 (although slight protrusion of sleeve 24 into the left ventricle can be tolerated). It is desired the sleeve not be so closely positioned near open ends 12, 14 such that tissue growth on the sleeve 24 can grow over and occlude the open ends 12, 14. It is anticipated that tissue growth on and into the sleeve 24 could result in a buildup of tissue beyond the sleeve 24 to a thickness of about at least 1 millimeter. It is desirable that such tissue growth does not extend over ends 12, 14. Accordingly, the sleeve 24 is spaced from ends of the tube 11 by a distance greater than an anticipated thickness of tissue growth extension beyond the sleeve 24.
  • The [0020] sleeve 24 is selected to induce tissue growth and attachment. Preferably, the sleeve 24 is formed of a fabric having biocompatible fibers defining interstitial spaces to receive tissue growth. An example of such a fabric is polyethylene terephthalate (such as polyester fabric sold by DuPont Company under the trademark Dacron). Such a fabric permits rapid tissue integration into the fabric thereby anchoring the fabric and, hence, the tube 11 to the patient's tissue.
  • While a fabric tissue growth inducing material is illustrated, other materials could be used. For example, the tissue growth inducing material could be sintered metal on the external surface of the tube [0021] 11. Sintered metal results in a porous surface to receive tissue growth. The area of the sintered metal will be spaced from ends 12, 14 to prevent tissue accumulation on the sintered area from growing over and blocking 12, 14. Alternatively, the exterior surface of the tube 11 can be roughened. The roughening can be in the form of a knurling or other roughened surface due to sandblasting or the application of sinter beads. The roughening results in surface protrusions and pitting, around which tissue may grow.
  • The implant [0022] 10 is placed with the first end 12 placed within the artery lumen 100 distal to an obstruction 105. Normal nourishing blood flow is in the direction of arrow A. The implant 10 passes through the heart wall 104 with the second end 14 positioned within the left ventricle 106 and spaced from the inner surface 103 of the heart wall 104 by 5 millimeters during periods of maximum heart wall thickness. The sleeve 24 is positioned opposing the heart wall 104 so that tissue from the heart wall 104 can grow into the sleeve 24.
  • With the positioning thus described, the [0023] first opening 12 opposes a wall 102 a of the artery 102. As a result, blood discharged from the opening 12 impinges directly upon the arterial wall 102 a.
  • The [0024] artery wall 102 a is a fragile layer of cells and fibers. Direct impingement of blood flow on the wall 102 a can damage the artery wall 102 a. As a healing response to such damage, a cellular matrix may develop and proliferate to such an extent that opening 12 or lumen 100 could occlude.
  • The present invention reduces the velocity of blood flow through the [0025] opening 12. Specifically, a flow restriction in the form of a narrowing 30 is placed within the conduit 11. The restriction 30 reduces blood flow below a velocity which would otherwise cause occluding trauma to the artery wall 102 a.
  • With the specific example given, the [0026] restriction 30 results in a narrow interior diameter D of about 0.5 millimeters. The narrow restriction 30 is positioned about 8 millimeters from end 14. The restriction 30 is formed by a venturi constriction formed within the conduit 11 adjacent end 14. The venturi may be formed by machining the conduit 11 from a solid blank of titanium. The venturi 30 has a shallow ramp 31 on a downstream side to avoid turbulence. Since an upstream side 33 is adjacent end 14, turbulence during reverse flow is not a serious concern.
  • With the [0027] restriction 30 as described, flow velocity out of end 12 is reduced below a level which would otherwise cause occluding trauma to the artery wall 102 a. By avoiding such trauma, a straight implant 10 can be provided which is more susceptible to minimally invasive and percutaneous implantation as well as being suitable for traditional surgical approaches.
  • Preferably, the blood flow velocity from [0028] end 12 is reduced to a velocity of normal blood flow within an artery 102 (about 30 ml/min.). Since the left ventricle 106 has a high maximum pressure, the pressure differential between the ventricle 106 and artery lumen 100 results in a higher than normal blood flow rate in the absence of the restriction 30.
  • Having disclosed the present invention in a preferred embodiment, it will be appreciated that modifications and equivalents may occur to one of ordinary skill in the art having the benefits of the teachings of the present invention. It is intended that such modifications shall be included within the scope of the claims appended hereto. For example, in the preferred embodiment shown, the tube [0029] 11 is a cylinder with circular cross-section. The tube 11 could have an oval cross-section at end 12 to provide a larger flow area and further reduce flow velocity. Also, while the tube 11 is preferably straight, the tube 11 could be bent so that the direction of blood flow from end 12 is not perpendicular to the arterial blood flow direction A.

Claims (12)

What is claimed:
1. A transmyocardial implant for establishing a blood flow path through a heart wall between a heart chamber and a lumen of a coronary vessel on said heart wall, said implant comprising:
a hollow conduit having an open first end and an open second end, said conduit sized to extend at least from said vessel through said heart wall and into said chamber, said conduit having a conduit wall defining a blood flow pathway within an interior of said conduit between said first and second ends;
said first and second ends mutually positioned for said first end to reside within said vessel and opposing a wall of said vessel when said conduit is placed within said heart wall with said second end protruding into said chamber;
said conduit wall formed of a material sufficiently rigid to resist deformation and closure of said pathway in response to contraction of said heart wall;
a flow restriction formed in said pathway for reducing a discharge velocity of blood flow discharged from said first end.
2. A transmyocardial implant according to
claim 1
 wherein said flow restriction is selected for said discharge velocity to be less than an occluding trauma inducing velocity.
3. A transmyocardial implant according to
claim 1
 wherein said restriction is a narrowing in said pathway positioned between enlarged crosssectional areas of said pathway.
4. A transmyocardial implant according to
claim 3
 wherein said pathway has a substantially straight longitudinal axis between said first and second ends.
5. A transmyocardial implant according to
claim 1
 wherein said conduit is sized for said first end to extend into said chamber beyond said heart wall.
6. A transmyocardial implant according to
claim 1
 further comprising a tissue growth inducing material surrounding said conduit wall.
7. A transmyocardial implant according to
claim 6
 wherein said tissue growth inducing material includes a plurality of fibers defining a plurality of interstitial spaces for receiving tissue growth and said tissue growth inducing material is biocompatible.
8. A transmyocardial implant according to
claim 7
 wherein said tissue growth inducing material is a polyester fabric.
9. A transmyocardial implant according to
claim 6
 wherein said tissue growth inducing material include a porous layer on said exterior of said conduit.
10. A transmyocardial implant according to
claim 9
 wherein said tissue growth inducing material includes a sintered layer.
11. A transmyocardial implant according to
claim 6
 wherein an external area of said conduit surrounded by said tissue growth inducing material is abraded.
12. A method for establishing a blood flow path through a heart wall between a heart chamber and a lumen of a coronary vessel on said heart wall, said method comprising:
forming a blood flow path from said vessel through said heart wall and into said chamber;
maintaining said blood flow path open during both systole and diastole;
restricting blood flow through said pathway to reducing a discharge velocity of blood flow discharged into said vessel.
US09/304,730 1999-05-04 1999-05-04 Transmyocardial implant with forward flow bias Expired - Fee Related US6409697B2 (en)

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Cited By (29)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2002030325A3 (en) * 2000-10-11 2002-08-22 Heartstent Corp Flexible transmyocardial implant
US6582444B2 (en) 1999-08-04 2003-06-24 Percardia, Inc. Blood flow conduit delivery system and method of use
US6605053B1 (en) 1999-09-10 2003-08-12 Percardia, Inc. Conduit designs and related methods for optimal flow control
US6605113B2 (en) 1999-08-04 2003-08-12 Percardia Inc. Vascular graft bypass
US6610100B2 (en) 1998-09-10 2003-08-26 Percardia, Inc. Designs for left ventricular conduit
US6641610B2 (en) 1998-09-10 2003-11-04 Percardia, Inc. Valve designs for left ventricular conduits
US6694983B2 (en) 1998-09-10 2004-02-24 Percardia, Inc. Delivery methods for left ventricular conduit
US6854467B2 (en) 2000-05-04 2005-02-15 Percardia, Inc. Methods and devices for delivering a ventricular stent
US6881199B2 (en) 1998-09-10 2005-04-19 Percardia, Inc. Left ventricular conduit with blood vessel graft
US6945949B2 (en) 1998-01-30 2005-09-20 Percardia, Inc. Left ventricular conduits to coronary arteries and methods for coronary bypass
US6964652B2 (en) 1999-08-04 2005-11-15 Percardia, Inc. Left ventricular conduits and methods for delivery
US6976990B2 (en) 2001-01-25 2005-12-20 Percardia, Inc. Intravascular ventriculocoronary bypass via a septal passageway
US7008397B2 (en) 2002-02-13 2006-03-07 Percardia, Inc. Cardiac implant and methods
US7033372B1 (en) 1999-08-04 2006-04-25 Percardia, Inc. Corkscrew reinforced left ventricle to coronary artery channel
US20060272384A1 (en) * 2004-05-21 2006-12-07 Lewis Darren F Flow sensor methods and apparatus
US7326219B2 (en) 2002-09-09 2008-02-05 Wilk Patent Development Device for placing transmyocardial implant
US9295393B2 (en) 2012-11-09 2016-03-29 Elwha Llc Embolism deflector
US10993805B2 (en) 2008-02-26 2021-05-04 Jenavalve Technology, Inc. Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
US11065138B2 (en) 2016-05-13 2021-07-20 Jenavalve Technology, Inc. Heart valve prosthesis delivery system and method for delivery of heart valve prosthesis with introducer sheath and loading system
US11185405B2 (en) 2013-08-30 2021-11-30 Jenavalve Technology, Inc. Radially collapsible frame for a prosthetic valve and method for manufacturing such a frame
US11197754B2 (en) 2017-01-27 2021-12-14 Jenavalve Technology, Inc. Heart valve mimicry
US11337800B2 (en) 2015-05-01 2022-05-24 Jenavalve Technology, Inc. Device and method with reduced pacemaker rate in heart valve replacement
US11357624B2 (en) 2007-04-13 2022-06-14 Jenavalve Technology, Inc. Medical device for treating a heart valve insufficiency
US11517431B2 (en) 2005-01-20 2022-12-06 Jenavalve Technology, Inc. Catheter system for implantation of prosthetic heart valves
US11564794B2 (en) 2008-02-26 2023-01-31 Jenavalve Technology, Inc. Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
US11589981B2 (en) 2010-05-25 2023-02-28 Jenavalve Technology, Inc. Prosthetic heart valve and transcatheter delivered endoprosthesis comprising a prosthetic heart valve and a stent
US12121461B2 (en) 2015-03-20 2024-10-22 Jenavalve Technology, Inc. Heart valve prosthesis delivery system and method for delivery of heart valve prosthesis with introducer sheath
US12171658B2 (en) 2022-11-09 2024-12-24 Jenavalve Technology, Inc. Catheter system for sequential deployment of an expandable implant
US12414854B2 (en) 2010-05-20 2025-09-16 Jenavalve Technology, Inc. Catheter system for introducing an expandable stent into the body of a patient

Families Citing this family (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2002524196A (en) 1998-09-10 2002-08-06 パーカーディア，インコーポレイティド Transmyocardial shunt for left ventricular revascularization and its mounting mechanism
US6409697B2 (en) * 1999-05-04 2002-06-25 Heartstent Corporation Transmyocardial implant with forward flow bias
US6949118B2 (en) 2002-01-16 2005-09-27 Percardia, Inc. Encased implant and methods
US20030216801A1 (en) * 2002-05-17 2003-11-20 Heartstent Corporation Transmyocardial implant with natural vessel graft and method
IES20030539A2 (en) * 2003-07-22 2005-05-18 Medtronic Vascular Connaught Stents and stent delivery system
US8496629B2 (en) * 2008-04-22 2013-07-30 Becton, Dickinson And Company Catheter hole having a flow breaking feature
US9211202B2 (en) * 2008-10-24 2015-12-15 Wisconsin Alumni Research Foundation Apparatus and method for treating an aneurysm
US9381112B1 (en) 2011-10-06 2016-07-05 William Eric Sponsell Bleb drainage device, ophthalmological product and methods
US8632489B1 (en) 2011-12-22 2014-01-21 A. Mateen Ahmed Implantable medical assembly and methods
MX2021014197A (en) 2019-05-21 2022-01-06 Djo Llc Height, depth and circumferential adjustment mechanisms for cervical collar.

Family Cites Families (212)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4546499A (en) * 1982-12-13 1985-10-15 Possis Medical, Inc. Method of supplying blood to blood receiving vessels
US4953553A (en) 1989-05-11 1990-09-04 Advanced Cardiovascular Systems, Inc. Pressure monitoring guidewire with a flexible distal portion
US6004261A (en) 1989-04-28 1999-12-21 C. R. Bard, Inc. Formed-in-place endovascular stent and delivery system
US5344426A (en) 1990-04-25 1994-09-06 Advanced Cardiovascular Systems, Inc. Method and system for stent delivery
US5389096A (en) 1990-12-18 1995-02-14 Advanced Cardiovascular Systems System and method for percutaneous myocardial revascularization
US5193546A (en) 1991-05-15 1993-03-16 Alexander Shaknovich Coronary intravascular ultrasound imaging method and apparatus
CA2074304C (en) 1991-08-02 1996-11-26 Cyril J. Schweich, Jr. Drug delivery catheter
CA2087132A1 (en) 1992-01-31 1993-08-01 Michael S. Williams Stent capable of attachment within a body lumen
US5470320A (en) 1992-04-10 1995-11-28 Tiefenbrun; Jonathan Method and related device for obtaining access to a hollow organ
US5758663A (en) 1992-04-10 1998-06-02 Wilk; Peter J. Coronary artery by-pass method
US5330486A (en) 1992-07-29 1994-07-19 Wilk Peter J Laparoscopic or endoscopic anastomosis technique and associated instruments
US5258008A (en) 1992-07-29 1993-11-02 Wilk Peter J Surgical stapling device and associated method
US5409019A (en) 1992-10-30 1995-04-25 Wilk; Peter J. Coronary artery by-pass method
US5287861A (en) 1992-10-30 1994-02-22 Wilk Peter J Coronary artery by-pass method and associated catheter
US5429144A (en) 1992-10-30 1995-07-04 Wilk; Peter J. Coronary artery by-pass method
US5797960A (en) 1993-02-22 1998-08-25 Stevens; John H. Method and apparatus for thoracoscopic intracardiac procedures
AU689094B2 (en) 1993-04-22 1998-03-26 C.R. Bard Inc. Non-migrating vascular prosthesis and minimally invasive placement system therefor
US5441515A (en) 1993-04-23 1995-08-15 Advanced Cardiovascular Systems, Inc. Ratcheting stent
ES2135520T3 (en) 1993-11-04 1999-11-01 Bard Inc C R NON-MIGRANT VASCULAR PROSTHESIS.
US5591197A (en) 1995-03-14 1997-01-07 Advanced Cardiovascular Systems, Inc. Expandable stent forming projecting barbs and method for deploying
US5571168A (en) 1995-04-05 1996-11-05 Scimed Lifesystems Inc Pull back stent delivery system
DE19514638C2 (en) 1995-04-20 1998-06-04 Peter Dr Med Boekstegers Device for the selective suction and retroinfusion of a fluid from or into body veins controlled by venous pressure
WO1996035469A1 (en) 1995-05-10 1996-11-14 Cardiogenesis Corporation System for treating or diagnosing heart tissue
US6251104B1 (en) 1995-05-10 2001-06-26 Eclipse Surgical Technologies, Inc. Guiding catheter system for ablating heart tissue
US6322548B1 (en) 1995-05-10 2001-11-27 Eclipse Surgical Technologies Delivery catheter system for heart chamber
WO1996039965A1 (en) 1995-06-07 1996-12-19 Cardiogenesis Corporation Surgical channel forming device with penetration limiter
US5840059A (en) 1995-06-07 1998-11-24 Cardiogenesis Corporation Therapeutic and diagnostic agent delivery
US6132451A (en) 1995-06-07 2000-10-17 Eclipse Surgical Technologies, Inc. Optical fiber for myocardial channel formation
US5728091A (en) 1995-06-07 1998-03-17 Cardiogenesis Corporation Optical fiber for myocardial channel formation
US6224584B1 (en) 1997-01-14 2001-05-01 Eclipse Surgical Technologies, Inc. Therapeutic and diagnostic agent delivery
US6156031A (en) 1995-08-09 2000-12-05 Eclipse Surgical Technologies Transmyocardial revascularization using radiofrequency energy
SE505125C2 (en) * 1995-10-10 1997-06-30 Gambro Ab Catheter, especially for peritoneal dialysis
DE69633411T2 (en) 1995-10-13 2005-10-20 Transvascular, Inc., Menlo Park METHOD AND DEVICE FOR PREVENTING ARTERIAL ATTRACTIONS AND / OR FOR CARRYING OUT OTHER TRANSVASCULAR INTERVENTIONS
US6302875B1 (en) 1996-10-11 2001-10-16 Transvascular, Inc. Catheters and related devices for forming passageways between blood vessels or other anatomical structures
US6375615B1 (en) 1995-10-13 2002-04-23 Transvascular, Inc. Tissue penetrating catheters having integral imaging transducers and their methods of use
US6283983B1 (en) 1995-10-13 2001-09-04 Transvascular, Inc. Percutaneous in-situ coronary bypass method and apparatus
US6726677B1 (en) 1995-10-13 2004-04-27 Transvascular, Inc. Stabilized tissue penetrating catheters
US6283951B1 (en) 1996-10-11 2001-09-04 Transvascular, Inc. Systems and methods for delivering drugs to selected locations within the body
ATE440559T1 (en) 1995-10-13 2009-09-15 Medtronic Vascular Inc DEVICE FOR INTERSTITIAL TRANSVASCULAR PROCEDURES
ATE248621T1 (en) 1996-01-19 2003-09-15 Scimed Life Systems Inc CATHETER WITH AN INCREASING RADIUS CURVE
CA2244080A1 (en) 1996-02-02 1997-08-07 Transvascular, Inc. Methods and apparatus for blocking flow through blood vessels
AU733341B2 (en) 1996-02-02 2001-05-10 Transvascular, Inc. A device, system and method for interstitial transvascular intervention
US6709444B1 (en) 1996-02-02 2004-03-23 Transvascular, Inc. Methods for bypassing total or near-total obstructions in arteries or other anatomical conduits
CN1216929A (en) 1996-02-02 1999-05-19 血管转换公司 Method and apparatus for blocking flow through blood vessels
US20030229366A1 (en) 1996-02-02 2003-12-11 Transvascular, Inc. Implantable lumen occluding devices and methods
US5713894A (en) 1996-02-27 1998-02-03 Murphy-Chutorian; Douglas Combined mechanical/optical system for transmyocardial revascularization
US5810836A (en) 1996-03-04 1998-09-22 Myocardial Stents, Inc. Device and method for trans myocardial revascularization (TMR)
US5830224A (en) 1996-03-15 1998-11-03 Beth Israel Deaconess Medical Center Catheter apparatus and methodology for generating a fistula on-demand between closely associated blood vessels at a pre-chosen anatomic site in-vivo
US5725523A (en) 1996-03-29 1998-03-10 Mueller; Richard L. Lateral-and posterior-aspect method and apparatus for laser-assisted transmyocardial revascularization and other surgical applications
US5725521A (en) 1996-03-29 1998-03-10 Eclipse Surgical Technologies, Inc. Depth stop apparatus and method for laser-assisted transmyocardial revascularization and other surgical applications
US6027497A (en) 1996-03-29 2000-02-22 Eclipse Surgical Technologies, Inc. TMR energy delivery system
US5766164A (en) 1996-07-03 1998-06-16 Eclipse Surgical Technologies, Inc. Contiguous, branched transmyocardial revascularization (TMR) channel, method and device
US5738680A (en) 1996-04-05 1998-04-14 Eclipse Surgical Technologies, Inc. Laser device with piercing tip for transmyocardial revascularization procedures
US6152918A (en) 1996-04-05 2000-11-28 Eclipse Surgical Technologies, Inc. Laser device with auto-piercing tip for myocardial revascularization procedures
US5782823A (en) 1996-04-05 1998-07-21 Eclipse Surgical Technologies, Inc. Laser device for transmyocardial revascularization procedures including means for enabling a formation of a pilot hole in the epicardium
SE509388C2 (en) 1996-05-17 1999-01-18 Jan Otto Solem Branching device for a blood vessel
US5662124A (en) 1996-06-19 1997-09-02 Wilk Patent Development Corp. Coronary artery by-pass method
SE509389C2 (en) 1996-07-24 1999-01-18 Solem Jan Otto Device for connecting the end of a first blood vessel to the side of a second blood vessel
US6569147B1 (en) 1996-07-26 2003-05-27 Kensey Nash Corporation Systems and methods of use for delivering beneficial agents for revascularizing stenotic bypass grafts and other occluded blood vessels and for other purposes
US6080170A (en) 1996-07-26 2000-06-27 Kensey Nash Corporation System and method of use for revascularizing stenotic bypass grafts and other occluded blood vessels
US6652546B1 (en) 1996-07-26 2003-11-25 Kensey Nash Corporation System and method of use for revascularizing stenotic bypass grafts and other occluded blood vessels
US5755682A (en) 1996-08-13 1998-05-26 Heartstent Corporation Method and apparatus for performing coronary artery bypass surgery
US6007543A (en) 1996-08-23 1999-12-28 Scimed Life Systems, Inc. Stent delivery system with stent securement means
WO1998008456A1 (en) * 1996-08-26 1998-03-05 Transvascular, Inc. Methods and apparatus for transmyocardial direct coronary revascularization
US5871495A (en) 1996-09-13 1999-02-16 Eclipse Surgical Technologies, Inc. Method and apparatus for mechanical transmyocardial revascularization of the heart
US5976164A (en) 1996-09-13 1999-11-02 Eclipse Surgical Technologies, Inc. Method and apparatus for myocardial revascularization and/or biopsy of the heart
US6186972B1 (en) 1996-09-16 2001-02-13 James A. Nelson Methods and apparatus for treating ischemic heart disease by providing transvenous myocardial perfusion
US6447539B1 (en) 1996-09-16 2002-09-10 Transvascular, Inc. Method and apparatus for treating ischemic heart disease by providing transvenous myocardial perfusion
US5655548A (en) 1996-09-16 1997-08-12 Circulation, Inc. Method for treatment of ischemic heart disease by providing transvenous myocardial perfusion
US6379319B1 (en) 1996-10-11 2002-04-30 Transvascular, Inc. Systems and methods for directing and snaring guidewires
US20020029079A1 (en) 1996-10-11 2002-03-07 Transvascular, Inc. Devices for forming and/or maintaining connections between adjacent anatomical conduits
WO1998016161A1 (en) 1996-10-11 1998-04-23 Transvascular, Inc. Methods and apparatus for bypassing arterial obstructions and/or performing other transvascular procedures
US6432127B1 (en) 1996-10-11 2002-08-13 Transvascular, Inc. Devices for forming and/or maintaining connections between adjacent anatomical conduits
US5931834A (en) 1996-10-15 1999-08-03 Eclipse Surgical Technologies, Inc. Method for non-synchronous laser-assisted myocardial revascularization
US5971993A (en) 1996-11-07 1999-10-26 Myocardial Stents, Inc. System for delivery of a trans myocardial device to a heart wall
US6258119B1 (en) 1996-11-07 2001-07-10 Myocardial Stents, Inc. Implant device for trans myocardial revascularization
US6053924A (en) 1996-11-07 2000-04-25 Hussein; Hany Device and method for trans myocardial revascularization
US6102926A (en) 1996-12-02 2000-08-15 Angiotrax, Inc. Apparatus for percutaneously performing myocardial revascularization having means for sensing tissue parameters and methods of use
US5910150A (en) 1996-12-02 1999-06-08 Angiotrax, Inc. Apparatus for performing surgery
US5899915A (en) 1996-12-02 1999-05-04 Angiotrax, Inc. Apparatus and method for intraoperatively performing surgery
US6120520A (en) 1997-05-27 2000-09-19 Angiotrax, Inc. Apparatus and methods for stimulating revascularization and/or tissue growth
US6165188A (en) 1996-12-02 2000-12-26 Angiotrax, Inc. Apparatus for percutaneously performing myocardial revascularization having controlled cutting depth and methods of use
US5925074A (en) 1996-12-03 1999-07-20 Atrium Medical Corporation Vascular endoprosthesis and method
US5944716A (en) 1996-12-09 1999-08-31 Scimed Life Systems, Inc. Radio frequency transmyocardial revascularization corer
US5807384A (en) 1996-12-20 1998-09-15 Eclipse Surgical Technologies, Inc. Transmyocardial revascularization (TMR) enhanced treatment for coronary artery disease
US6067988A (en) 1996-12-26 2000-05-30 Eclipse Surgical Technologies, Inc. Method for creation of drug delivery and/or stimulation pockets in myocardium
US5999678A (en) 1996-12-27 1999-12-07 Eclipse Surgical Technologies, Inc. Laser delivery means adapted for drug delivery
US5925012A (en) 1996-12-27 1999-07-20 Eclipse Surgical Technologies, Inc. Laser assisted drug delivery
CA2225521C (en) 1996-12-27 2004-04-06 Eclipse Surgical Technologies, Inc. Laser assisted drug delivery apparatus
US20040088042A1 (en) 1997-01-31 2004-05-06 Transvascular, Inc. Devices for forming and/or maintaining connections between adjacent anatomical conduits
US6508825B1 (en) 1997-02-28 2003-01-21 Lumend, Inc. Apparatus for treating vascular occlusions
US6217549B1 (en) 1997-02-28 2001-04-17 Lumend, Inc. Methods and apparatus for treating vascular occlusions
US6010449A (en) 1997-02-28 2000-01-04 Lumend, Inc. Intravascular catheter system for treating a vascular occlusion
US5968064A (en) 1997-02-28 1999-10-19 Lumend, Inc. Catheter system for treating a vascular occlusion
US5968059A (en) 1997-03-06 1999-10-19 Scimed Life Systems, Inc. Transmyocardial revascularization catheter and method
US6155264A (en) 1997-03-06 2000-12-05 Scimed Life Systems, Inc. Percutaneous bypass by tunneling through vessel wall
US6026814A (en) 1997-03-06 2000-02-22 Scimed Life Systems, Inc. System and method for percutaneous coronary artery bypass
US5938632A (en) 1997-03-06 1999-08-17 Scimed Life Systems, Inc. Radiofrequency transmyocardial revascularization apparatus and method
US6045565A (en) 1997-11-04 2000-04-04 Scimed Life Systems, Inc. Percutaneous myocardial revascularization growth factor mediums and method
US6035856A (en) 1997-03-06 2000-03-14 Scimed Life Systems Percutaneous bypass with branching vessel
US6086534A (en) 1997-03-07 2000-07-11 Cardiogenesis Corporation Apparatus and method of myocardial revascularization using ultrasonic pulse-echo distance ranging
US6093177A (en) 1997-03-07 2000-07-25 Cardiogenesis Corporation Catheter with flexible intermediate section
US5876373A (en) 1997-04-04 1999-03-02 Eclipse Surgical Technologies, Inc. Steerable catheter
WO1998046115A2 (en) 1997-04-11 1998-10-22 Transvascular, Inc. Methods and apparatus for transmyocardial direct coronary revascularization
US6024703A (en) 1997-05-07 2000-02-15 Eclipse Surgical Technologies, Inc. Ultrasound device for axial ranging
WO1998049964A1 (en) 1997-05-08 1998-11-12 C. R. Bard, Inc. Tmr stent and delivery system
US7329277B2 (en) 1997-06-13 2008-02-12 Orbusneich Medical, Inc. Stent having helical elements
EP0884029B1 (en) 1997-06-13 2004-12-22 Gary J. Becker Expandable intraluminal endoprosthesis
US6443158B1 (en) 1997-06-19 2002-09-03 Scimed Life Systems, Inc. Percutaneous coronary artery bypass through a venous vessel
US6092526A (en) 1997-06-19 2000-07-25 Scimed Life Systems, Inc. Percutaneous chamber-to-artery bypass
US6213126B1 (en) 1997-06-19 2001-04-10 Scimed Life Systems, Inc. Percutaneous artery to artery bypass using heart tissue as a portion of a bypass conduit
US6071292A (en) 1997-06-28 2000-06-06 Transvascular, Inc. Transluminal methods and devices for closing, forming attachments to, and/or forming anastomotic junctions in, luminal anatomical structures
EP1001708A1 (en) 1997-08-07 2000-05-24 Cardiogenesis Corporation System and method of intra-operative myocardial revascularization using pulsed sonic energy
US5908029A (en) 1997-08-15 1999-06-01 Heartstent Corporation Coronary artery bypass with reverse flow
US5922022A (en) 1997-09-04 1999-07-13 Kensey Nash Corporation Bifurcated connector system for coronary bypass grafts and methods of use
US6565594B1 (en) 1997-09-24 2003-05-20 Atrium Medical Corporation Tunneling device
CA2305333A1 (en) 1997-10-02 1999-04-15 Cardiogenesis Corporation Transmyocardial revascularization using radiofrequency energy
US6102941A (en) 1997-10-06 2000-08-15 Heartstent Corporation Transmyocardial implant with coronary ingrowth
US5984956A (en) * 1997-10-06 1999-11-16 Heartstent Corporation Transmyocardial implant
US5980548A (en) 1997-10-29 1999-11-09 Kensey Nash Corporation Transmyocardial revascularization system
US6063082A (en) 1997-11-04 2000-05-16 Scimed Life Systems, Inc. Percutaneous myocardial revascularization basket delivery system and radiofrequency therapeutic device
US6416490B1 (en) 1997-11-04 2002-07-09 Scimed Life Systems, Inc. PMR device and method
US6056743A (en) 1997-11-04 2000-05-02 Scimed Life Systems, Inc. Percutaneous myocardial revascularization device and method
US6183432B1 (en) 1997-11-13 2001-02-06 Lumend, Inc. Guidewire and catheter with rotating and reciprocating symmetrical or asymmetrical distal tip
US6330884B1 (en) 1997-11-14 2001-12-18 Transvascular, Inc. Deformable scaffolding multicellular stent
US6156029A (en) 1997-11-25 2000-12-05 Eclipse Surgical Technologies, Inc. Selective treatment of endocardial/myocardial boundary
US6764461B2 (en) 1997-12-01 2004-07-20 Scimed Life Systems, Inc. Catheter system for the delivery of a low volume bolus
US6197324B1 (en) 1997-12-18 2001-03-06 C. R. Bard, Inc. System and methods for local delivery of an agent
US6251418B1 (en) 1997-12-18 2001-06-26 C.R. Bard, Inc. Systems and methods for local delivery of an agent
US6217527B1 (en) 1998-09-30 2001-04-17 Lumend, Inc. Methods and apparatus for crossing vascular occlusions
US6231546B1 (en) 1998-01-13 2001-05-15 Lumend, Inc. Methods and apparatus for crossing total occlusions in blood vessels
AU2004999A (en) 1998-01-15 1999-08-02 Lumend, Inc. Catheter apparatus for guided transvascular treatment of arterial occlusions
US6081738A (en) 1998-01-15 2000-06-27 Lumend, Inc. Method and apparatus for the guided bypass of coronary occlusions
AU1927399A (en) 1998-01-16 1999-08-02 Lumend, Inc. Catheter apparatus for treating arterial occlusions
US6250305B1 (en) 1998-01-20 2001-06-26 Heartstent Corporation Method for using a flexible transmyocardial implant
US6200311B1 (en) 1998-01-20 2001-03-13 Eclipse Surgical Technologies, Inc. Minimally invasive TMR device
US6015405A (en) 1998-01-20 2000-01-18 Tricardia, L.L.C. Device for forming holes in tissue
US6214041B1 (en) 1998-01-20 2001-04-10 Heartstent Corporation Transmyocardial implant with septal perfusion
US6193734B1 (en) 1998-01-23 2001-02-27 Heartport, Inc. System for performing vascular anastomoses
AU757647B2 (en) 1998-01-30 2003-02-27 Wilk Patent Development Corporation Transmyocardial coronary artery bypass and revascularization
WO2000015275A2 (en) 1998-09-10 2000-03-23 Percardia, Inc. Body fluid shunt device and method of use
US20020144696A1 (en) 1998-02-13 2002-10-10 A. Adam Sharkawy Conduits for use in placing a target vessel in fluid communication with a source of blood
US20010041902A1 (en) 1998-02-13 2001-11-15 Michael J. Lynch Anastomotic methods and devices for placing a target vessel in fluid communication with a source of blood
US6808498B2 (en) 1998-02-13 2004-10-26 Ventrica, Inc. Placing a guide member into a heart chamber through a coronary vessel and delivering devices for placing the coronary vessel in communication with the heart chamber
US6352543B1 (en) 2000-04-29 2002-03-05 Ventrica, Inc. Methods for forming anastomoses using magnetic force
WO1999040868A1 (en) 1998-02-13 1999-08-19 Ventrica, Inc. Methods and devices providing transmyocardial blood flow to the arterial vascular system of the heart
US6651670B2 (en) 1998-02-13 2003-11-25 Ventrica, Inc. Delivering a conduit into a heart wall to place a coronary vessel in communication with a heart chamber and removing tissue from the vessel or heart wall to facilitate such communication
US6398798B2 (en) 1998-02-28 2002-06-04 Lumend, Inc. Catheter system for treating a vascular occlusion
US6093185A (en) 1998-03-05 2000-07-25 Scimed Life Systems, Inc. Expandable PMR device and method
DE99911188T1 (en) 1998-03-05 2005-06-23 Boston Scientific Ltd., St. Michael EXPANDABLE DEVICE FOR TRANSMYOCARDIAL REVASCULARIZATION AND METHOD
AU3453299A (en) 1998-03-24 1999-10-18 Lumend, Inc. Improved guidewire, catheter and method of crossing tight intravascular occlusions using same
AU762604B2 (en) 1998-03-31 2003-06-26 Transvascular, Inc. Catheters, systems and methods for percutaneous in situ arterio-venous bypass
US6561998B1 (en) 1998-04-07 2003-05-13 Transvascular, Inc. Transluminal devices, systems and methods for enlarging interstitial penetration tracts
US6076529A (en) * 1998-04-20 2000-06-20 Heartstent Corporation Transmyocardial implant with inserted vessel
US6029672A (en) 1998-04-20 2000-02-29 Heartstent Corporation Transmyocardial implant procedure and tools
US6296655B1 (en) 1998-04-27 2001-10-02 Advanced Cardiovascular Systems, Inc. Catheter balloon with biased multiple wings
US20010027287A1 (en) 1998-05-26 2001-10-04 Trans Vascular, Inc. Apparatus for providing coronary retroperfusion and/or left ventricular assist and methods of use
US7083588B1 (en) 1998-05-26 2006-08-01 Medtronic Vascular, Inc. Apparatus for providing coronary retroperfusion and methods of use
US6113823A (en) * 1998-06-09 2000-09-05 Heartstent Corporation Pyrolytic carbon transmyocardial implant
US5980533A (en) 1998-06-09 1999-11-09 Scimed Life Systems, Inc. Stent delivery system
US6285903B1 (en) 1998-06-30 2001-09-04 Eclipse Surgical Technologies, Inc. Intracorporeal device with radiopaque marker
US6036697A (en) 1998-07-09 2000-03-14 Scimed Life Systems, Inc. Balloon catheter with balloon inflation at distal end of balloon
US6171251B1 (en) 1998-07-14 2001-01-09 Eclipse Surgical Technologies, Inc. Method and apparatus for optimizing direct vessel implants for myocardial revascularization
US6053942A (en) * 1998-08-18 2000-04-25 Heartstent Corporation Transmyocardial implant with coronary stent
US6406488B1 (en) 1998-08-27 2002-06-18 Heartstent Corporation Healing transmyocardial implant
US6139541A (en) 1998-09-02 2000-10-31 Heartstent Corporation Guide for transmyocardial implant
US6251061B1 (en) 1998-09-09 2001-06-26 Scimed Life Systems, Inc. Cardiac assist device using field controlled fluid
NO984143L (en) 1998-09-09 2000-03-10 Norsk Hydro As New process for producing surface modifying substances
NO984144L (en) 1998-09-09 2000-03-10 Carmeda Ab Composition comprising heparin as a non-thrombogenic surface coating
US6254564B1 (en) * 1998-09-10 2001-07-03 Percardia, Inc. Left ventricular conduit with blood vessel graft
US6641610B2 (en) 1998-09-10 2003-11-04 Percardia, Inc. Valve designs for left ventricular conduits
JP2002524196A (en) * 1998-09-10 2002-08-06 パーカーディア，インコーポレイティド Transmyocardial shunt for left ventricular revascularization and its mounting mechanism
AU6384699A (en) * 1998-09-10 2000-04-03 Percardia, Inc. Tmr shunt
US6290728B1 (en) * 1998-09-10 2001-09-18 Percardia, Inc. Designs for left ventricular conduit
WO2000015146A1 (en) 1998-09-10 2000-03-23 Percardia, Inc. Transmyocardial shunt for left ventricular revascularization
US6196230B1 (en) 1998-09-10 2001-03-06 Percardia, Inc. Stent delivery system and method of use
US6261304B1 (en) 1998-09-10 2001-07-17 Percardia, Inc. Delivery methods for left ventricular conduit
US6197050B1 (en) 1998-09-14 2001-03-06 Heartstent Corporation Transmyocardial implant with compliance collar
WO2000018331A2 (en) 1998-09-29 2000-04-06 C. R. Bard, Inc. Drug delivery systems
US6248112B1 (en) 1998-09-30 2001-06-19 C. R. Bard, Inc. Implant delivery system
US6251079B1 (en) 1998-09-30 2001-06-26 C. R. Bard, Inc. Transthoracic drug delivery device
US6432126B1 (en) 1998-09-30 2002-08-13 C.R. Bard, Inc. Flexible vascular inducing implants
US6458092B1 (en) 1998-09-30 2002-10-01 C. R. Bard, Inc. Vascular inducing implants
US6283935B1 (en) 1998-09-30 2001-09-04 Hearten Medical Ultrasonic device for providing reversible tissue damage to heart muscle
EP1121067A1 (en) 1998-10-13 2001-08-08 Ventrica, Inc. Devices and methods for use in performing transmyocardial coronary bypass
US6692520B1 (en) 1998-12-15 2004-02-17 C. R. Bard, Inc. Systems and methods for imbedded intramuscular implants
US6363938B2 (en) 1998-12-22 2002-04-02 Angiotrax, Inc. Methods and apparatus for perfusing tissue and/or stimulating revascularization and tissue growth
EP1027870B1 (en) 1999-01-12 2005-03-30 Orbus Medical Technologies, Inc. Expandable intraluminal endoprosthesis
EP1020166A1 (en) 1999-01-12 2000-07-19 Orbus Medical Technologies, Inc. Expandable intraluminal endoprosthesis
US6193726B1 (en) 1999-01-15 2001-02-27 Heartstent Corporation Insertion tool for transmyocardial implant
US7025773B2 (en) 1999-01-15 2006-04-11 Medtronic, Inc. Methods and devices for placing a conduit in fluid communication with a target vessel
CA2360587A1 (en) 1999-01-15 2000-07-20 Darin C. Gittings Methods and devices for forming vascular anastomoses
AU2966900A (en) 1999-01-15 2000-08-01 Ventrica, Inc. Methods and devices for bypassing an obstructed target vessel by placing the vessel in communication with a heart chamber containing blood
US7637886B2 (en) 1999-01-25 2009-12-29 Atrium Medical Corporation Expandable fluoropolymer device and method of making
EP1148899B1 (en) 1999-01-25 2006-04-05 Atrium Medical Corporation Expandable fluoropolymer device for delivery of therapeutic agents
US6395208B1 (en) 1999-01-25 2002-05-28 Atrium Medical Corporation Method of making an expandable fluoropolymer device
US6475226B1 (en) 1999-02-03 2002-11-05 Scimed Life Systems, Inc. Percutaneous bypass apparatus and method
WO2000049952A1 (en) 1999-02-23 2000-08-31 Scimed Life Systems, Inc. Method of using focused pressure fronts in myocardial revascularization
US6217575B1 (en) 1999-02-24 2001-04-17 Scimed Life Systems, Inc. PMR catheter
US6468271B1 (en) 1999-02-24 2002-10-22 Scimed Life Systems, Inc. Device and method for percutaneous myocardial revascularization
US6231551B1 (en) 1999-03-01 2001-05-15 Coaxia, Inc. Partial aortic occlusion devices and methods for cerebral perfusion augmentation
US5976155A (en) 1999-03-05 1999-11-02 Advanced Cardiovascular Systems, Inc. System for removably securing a stent on a catheter assembly and method of use
US6432119B1 (en) 1999-03-17 2002-08-13 Angiotrax, Inc. Apparatus and methods for performing percutaneous myocardial revascularization and stimulating angiogenesis using autologous materials
US6569145B1 (en) 1999-03-25 2003-05-27 Transvascular, Inc. Pressure-controlled continuous coronary sinus occlusion device and methods of use
CA2372149A1 (en) 1999-05-03 2000-11-09 Dean F. Carson Methods and devices for placing a conduit in fluid communication with a target vessel
AU4982500A (en) 1999-05-03 2000-11-17 Ventrica, Inc. Methods and devices for forming a conduit between a target vessel and a blood source
US20040044392A1 (en) 1999-05-03 2004-03-04 Jomed Gmbh Stent catheter system
US6409697B2 (en) * 1999-05-04 2002-06-25 Heartstent Corporation Transmyocardial implant with forward flow bias
US6182668B1 (en) * 1999-05-13 2001-02-06 Heartstent Corporation Transmyocardial implant with induced tissue flap
US6709427B1 (en) 1999-08-05 2004-03-23 Kensey Nash Corporation Systems and methods for delivering agents into targeted tissue of a living being
US6605053B1 (en) 1999-09-10 2003-08-12 Percardia, Inc. Conduit designs and related methods for optimal flow control
EP1088564A1 (en) 1999-09-30 2001-04-04 Orbus Medical Technologies, Inc. Intraluminal device, coating for such device, as well as a method for preparing the intraluminal device

Cited By (45)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6945949B2 (en) 1998-01-30 2005-09-20 Percardia, Inc. Left ventricular conduits to coronary arteries and methods for coronary bypass
US7294115B1 (en) 1998-01-30 2007-11-13 Percardia, Inc. Methods of providing direct blood flow between a heart chamber and a coronary vessel
US6949080B2 (en) 1998-01-30 2005-09-27 Percardia, Inc. Left ventricular conduits to coronary arteries and methods for coronary bypass
US7704222B2 (en) 1998-09-10 2010-04-27 Jenavalve Technology, Inc. Methods and conduits for flowing blood from a heart chamber to a blood vessel
US7011095B2 (en) 1998-09-10 2006-03-14 Percardia, Inc. Valve designs for left ventricular conduits
US8597226B2 (en) 1998-09-10 2013-12-03 Jenavalve Technology, Inc. Methods and conduits for flowing blood from a heart chamber to a blood vessel
US6694983B2 (en) 1998-09-10 2004-02-24 Percardia, Inc. Delivery methods for left ventricular conduit
US7347867B2 (en) 1998-09-10 2008-03-25 Wilk Patent And Development Corporation Designs for left ventricular conduit
US6881199B2 (en) 1998-09-10 2005-04-19 Percardia, Inc. Left ventricular conduit with blood vessel graft
US8216174B2 (en) 1998-09-10 2012-07-10 Jenavalve Technology, Inc. Methods and conduits for flowing blood from a heart chamber to a blood vessel
US6641610B2 (en) 1998-09-10 2003-11-04 Percardia, Inc. Valve designs for left ventricular conduits
US6953481B2 (en) 1998-09-10 2005-10-11 Percardia, Inc. Designs for left ventricular conduit
US6610100B2 (en) 1998-09-10 2003-08-26 Percardia, Inc. Designs for left ventricular conduit
US7101402B2 (en) 1998-09-10 2006-09-05 Percardia, Inc. Designs for left ventricular conduit
US7736327B2 (en) 1998-09-10 2010-06-15 Jenavalve Technology, Inc. Methods and conduits for flowing blood from a heart chamber to a blood vessel
US6964652B2 (en) 1999-08-04 2005-11-15 Percardia, Inc. Left ventricular conduits and methods for delivery
US7033372B1 (en) 1999-08-04 2006-04-25 Percardia, Inc. Corkscrew reinforced left ventricle to coronary artery channel
US6582444B2 (en) 1999-08-04 2003-06-24 Percardia, Inc. Blood flow conduit delivery system and method of use
US6605113B2 (en) 1999-08-04 2003-08-12 Percardia Inc. Vascular graft bypass
US6605053B1 (en) 1999-09-10 2003-08-12 Percardia, Inc. Conduit designs and related methods for optimal flow control
US6854467B2 (en) 2000-05-04 2005-02-15 Percardia, Inc. Methods and devices for delivering a ventricular stent
WO2002030325A3 (en) * 2000-10-11 2002-08-22 Heartstent Corp Flexible transmyocardial implant
US6976990B2 (en) 2001-01-25 2005-12-20 Percardia, Inc. Intravascular ventriculocoronary bypass via a septal passageway
US7008397B2 (en) 2002-02-13 2006-03-07 Percardia, Inc. Cardiac implant and methods
US7326219B2 (en) 2002-09-09 2008-02-05 Wilk Patent Development Device for placing transmyocardial implant
US20060272384A1 (en) * 2004-05-21 2006-12-07 Lewis Darren F Flow sensor methods and apparatus
US11517431B2 (en) 2005-01-20 2022-12-06 Jenavalve Technology, Inc. Catheter system for implantation of prosthetic heart valves
US11357624B2 (en) 2007-04-13 2022-06-14 Jenavalve Technology, Inc. Medical device for treating a heart valve insufficiency
US11564794B2 (en) 2008-02-26 2023-01-31 Jenavalve Technology, Inc. Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
US10993805B2 (en) 2008-02-26 2021-05-04 Jenavalve Technology, Inc. Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
US11154398B2 (en) 2008-02-26 2021-10-26 JenaValve Technology. Inc. Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
US12232957B2 (en) 2008-02-26 2025-02-25 Jenavalve Technology, Inc. Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient
US12414854B2 (en) 2010-05-20 2025-09-16 Jenavalve Technology, Inc. Catheter system for introducing an expandable stent into the body of a patient
US11589981B2 (en) 2010-05-25 2023-02-28 Jenavalve Technology, Inc. Prosthetic heart valve and transcatheter delivered endoprosthesis comprising a prosthetic heart valve and a stent
US9414752B2 (en) 2012-11-09 2016-08-16 Elwha Llc Embolism deflector
US9295393B2 (en) 2012-11-09 2016-03-29 Elwha Llc Embolism deflector
US11185405B2 (en) 2013-08-30 2021-11-30 Jenavalve Technology, Inc. Radially collapsible frame for a prosthetic valve and method for manufacturing such a frame
US12318281B2 (en) 2013-08-30 2025-06-03 Jenavalve Technology, Inc. Radially collapsible frame for a prosthetic valve and method for manufacturing such a frame
US12121461B2 (en) 2015-03-20 2024-10-22 Jenavalve Technology, Inc. Heart valve prosthesis delivery system and method for delivery of heart valve prosthesis with introducer sheath
US11337800B2 (en) 2015-05-01 2022-05-24 Jenavalve Technology, Inc. Device and method with reduced pacemaker rate in heart valve replacement
US12343255B2 (en) 2015-05-01 2025-07-01 Jenavalve Technology, Inc. Device and method with reduced pacemaker rate in heart valve replacement
US11065138B2 (en) 2016-05-13 2021-07-20 Jenavalve Technology, Inc. Heart valve prosthesis delivery system and method for delivery of heart valve prosthesis with introducer sheath and loading system
US11197754B2 (en) 2017-01-27 2021-12-14 Jenavalve Technology, Inc. Heart valve mimicry
US12433745B2 (en) 2017-01-27 2025-10-07 Jenavalve Technology, Inc. Heart valve mimicry
US12171658B2 (en) 2022-11-09 2024-12-24 Jenavalve Technology, Inc. Catheter system for sequential deployment of an expandable implant

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