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WO2004110307A2 - Gaine deformante pour un dispositif d'activation cardiaque - Google Patents

Gaine deformante pour un dispositif d'activation cardiaque Download PDF

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Publication number
WO2004110307A2
WO2004110307A2 PCT/US2004/018298 US2004018298W WO2004110307A2 WO 2004110307 A2 WO2004110307 A2 WO 2004110307A2 US 2004018298 W US2004018298 W US 2004018298W WO 2004110307 A2 WO2004110307 A2 WO 2004110307A2
Authority
WO
WIPO (PCT)
Prior art keywords
jacket
heart
chamber
free wall
engaging
Prior art date
Legal status (The legal status 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 status listed.)
Ceased
Application number
PCT/US2004/018298
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English (en)
Other versions
WO2004110307A3 (fr
Inventor
David Boyd Melvin
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
University of Cincinnati
Original Assignee
University of Cincinnati
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
Application filed by University of Cincinnati filed Critical University of Cincinnati
Priority to EP04754797A priority Critical patent/EP1631348A4/fr
Publication of WO2004110307A2 publication Critical patent/WO2004110307A2/fr
Publication of WO2004110307A3 publication Critical patent/WO2004110307A3/fr
Priority to US11/298,428 priority patent/US7850729B2/en
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • 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
    • A61F2/2478—Passive devices for improving the function of the heart muscle, i.e. devices for reshaping the external surface of the heart, e.g. bags, strips or bands
    • A61F2/2481—Devices outside the heart wall, e.g. bags, strips or bands
    • 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
    • A61F2/2442—Annuloplasty rings or inserts for correcting the valve shape; Implants for improving the function of a native heart valve

Definitions

  • This invention relates generally to assisting the natural heart in operation and, more specifically, to components to assist in actuating one or more walls of the natural heart.
  • the human circulatory system is critical for survival and systematically provides nutrients and oxygen as well as removing harmful waste products from all parts of the body.
  • the heart is a critical component of the circulatory system in that it provides pumping power.
  • the right side of the heart receives blood from the 'systemic circulation' (all the body except the lungs) and pumps it into the 'pulmonary circulation' (lungs), whereas the left side of the heart receives blood from the lungs and pumps it back into the systemic circulation.
  • Each side comprises an inflow or collecting chamber with a thin muscular wall, its 'atrium' and a thicker, more powerful muscular pumping chamber, its 'ventricle', which alters volume cyclically due to contraction and relaxation of the muscles in its walls.
  • One-way valves are positioned in the passage way between the left and right atrium and the corresponding ventricle, and between each ventricle and the large arteries, which conduct blood into the systemic or pulmonary circulation, respectively. Because of this arrangement, each atrium may gently contract, causing blood to flow across the 'atrioventricular' valve into the ventricle, with that valve then closing to prevent return. Similarly, each ventricle may then forcefully contract, causing blood to flow across the outflow valves into the systemic or pulmonary circulation.
  • a physical ailment or condition which compromises the effective muscular contraction in the walls of one or more chambers of the heart can therefore be particularly critical and may result in a condition which must be medically remedied if the person is to long survive.
  • the muscle of the heart may degrade for various reasons to a point where the heart can no longer provide sufficient circulation of blood to maintain the health of a person at an acceptable level.
  • the heart may degrade to the point of failure and not been be able to sustain life.
  • solutions are offered to maintain the circulation. Some of these solutions involve replacing the heart. Some involve assisting it with mechanical devices. Some are directed to maintain operation of the existing heart.
  • the heart may be removed and replaced with either a mechanical device (a total artificial heart) or a natural heart from another human or an animal (heart transplant).
  • Artificial heart use has been complicated by consequences of blood clots forming on the internal lining. The most serious consequence is a breaking loose of such clots, which are then propelled into various parts of the circulation. In the event of such a clot being propelled into the brain, a disabling or fatal stroke may result.
  • human heart transplantation is limited by rejection, a response of the body's immune system, this may usually be controlled by medications to the degree that half of all recipients survive at least ten years, generally with acceptable health and function.
  • a more serious limitation is numbers of available donors. These are usually accidental death victims whose hearts maintain function despite brain death. Currently these are available for less than 1 to 2 percent of potential beneficiaries (about 2000 per year in the United States for over 200,000 people dying of heart failure annually in the same country, for example).
  • the heart may be assisted by mechanical auxiliary pumps. These are of three general types: counterpulsators, pulsatile assist systems, and nonpulsatile assist systems.
  • Counterpulsators such as intraaortic balloon pump cyclically remove or displace blood from the arterial system in synchrony with the natural heart's beat and, without valves, may perform substantial work for a weakened heart.
  • Pulsatile assist systems ventricular assist devices are similar to artificial hearts except that they are used in addition to one or both sides of the heart rather than instead of the heart. They receive blood from either the atrium or ventricle on one side of the circulation and pump it into that side's arterial system, relieving the ventricle of part of its volume load, pressure load, or both.
  • Nonpulsatile assist systems are rotary pumps, either centrifugal, axial flow, or a combination, that similarly pump blood in a steady flow from atrium or ventricle into circulatory systems.
  • AN of these mechanical pumps have extensive non-living material surfaces that contact blood. The complications of blood clotting with stroke or other serious aftermaths, described with artificial hearts also occur with these mechanical auxiliary pumps.
  • This chamber restriction is important because the two sides of the circulation require far different pressures for acceptable function (usually the systemic pressure is 3 to 5 times as high as is the pulmonary pressure). Compressive patterns of either muscle wraps or mechanical devices may also distort heart valves, which can lead to valve leakage.
  • the coupling between the internal and external framework elements of the actuation system occurs across tissue.
  • transmural cords extend between semi rigid internal valve annular rings and an external transverse arc of a yoke coupled to the outside of the heart. Due to over-tightening of the cords when they are positioned, and/or to swelling of the tissue afterward, there may be compression of myocardial tissue and traversing of coronary artery branches.
  • the coupling between discrete actuating components and discrete framework components, both external to the heart have potential of damaging or abrading the surface of the heart during motion.
  • the active jacket is a preferred embodiment of the basal cushion, which extends over the free ventricular wall of one or both ventricles as well as over the ventricular base.
  • it is a thin (generally 0.5 to 8.0 mm thick), flexurally elastic jacket substantially encompassing the epicardial surface of at least one chamber of the natural heart.
  • 'Flexurally elastic' in this description is defined as having a measurable bending stiffness (neither flaccid nor absolutely rigid) in a tangent plane in at least part of the structure. Fabrication methods and materials may be varied as required in any location to meet required specifications.
  • the jacket may also be longitudinally elastic in tension and/or compression in at least one direction at one or more locations.
  • Figure 1 is a non-limiting example of an active jacket configured for the left ventricle, alone.
  • Figure 2 is the same jacket in place on an intact heart in diastole.
  • Figure 3 is the jacket in place on an intact heart in systole.
  • Figure 4 is a preferred embodiment in which a serpentine pattern spring wire grid structure is clad in polymeric padding.
  • Figure 5 is a nonlimiting example showing close detail of an alternate construction in which spring elements make up all of the jacket's structure.
  • Figure 6 is a whole jacket for left ventricular application of the structure shown in figures 13.
  • Figure 7 shows a textured region on part of the heart-facing surface of a jacket.
  • Figure 8 is a left-side device jacket suspended above the heart while sutures exiting from internal septal-supporting components are placed circumferentially in the margins of the jacket, both its free-wall and its basal sections.
  • Figure 9 is the device of figure 16 after it has been lowered into position with sutures tied or otherwise secured.
  • Figure 10a is a laminar tension-indicator surface shown in exploded view.
  • Figure 10b is a laminar tension indicator with a suture tied sufficiently tight.
  • Figure 10c is a laminar tension-indicator surface with a suture pulled excessively tight, indicating need to loosen before completing knot.
  • Figure 11a is an elastic tension-indicator with two suture ends loosely looped through.
  • Figure 11 b is an elastic tension-indicator with two suture ends looped through and knot tightened to appropriate tension.
  • Figure 12' is a great vessel sleeve in perspective view.
  • Figure 13 is a great vessel sleeve in sectional view.
  • Figure 14 is a great vessel sleeve in sectional view mounted on the aorta.
  • Figure 15 is patch repair of the medial wall defect in the right atrium that results from separation of the two atria in which the previous intra- atrial septum has been left as a new medial wall for the left atrium.
  • Figure 16 is two perspective views of the atrial collar, showing the ventricular (above) and atrial (below) surfaces, respectively.
  • Figure 17 is a sectional view of the atrial collar on the base of the left atrium.
  • Aortic sleeve a protective tubular extension along the external surface of the proximal aorta. This provides a smooth surface over vulnerable area of the aortic sinuses and proximal coronaries.
  • Polymer padding composed preferably of polyester fiber, which may be impregnated with an elastomer such as silicone rubber or a urethane.
  • thin soft elastomer that may have suspended colloid or gas to increase diffusion except when compressed
  • a cushioned, flexurally elastic jacket is configured to rest on the extracardiac border of at least one cardiac chamber, including the basal margin.
  • Figure 1 is a non- limiting example of such an active jacket [39] configured for the left ventricle alone.
  • the jacket has an inner, or heart-facing surface [40] and an outer surface [41].
  • the jacket generally has a free-wall [42] section and a basal section [43] each of which may extend over the left, right, or both sides of the heart — although the illustration in figures shown is for the left ventricle.
  • the free-wall section of the jacket is configured to fit over the free wall of the ventricle, and the basal section over the ventricle's base, surrounding its inflow and outflow valves.
  • the free-wall section of the jacket 39 may include one or more actuator elements 38, such as mechanical actuator elements, for deforming the free wall section to assist or replace the natural operation of the heart.
  • the actuator element 38 will be coupled to a suitable actuator system 37 ⁇ for providing the power and control of the actuation, such as to exert a force and empty the heart chamber (systole).
  • the free-wall section of the jacket whether part of a left, a right, or biventricular device, since it has flexural elasticity as described above, exerts an outward force on pericardium or other tissues surrounding the ventricular free wall during refilling (diastole). This is due to passive elastic recoil derived from energy stored during active ejection (systole).
  • the outward force may be transmitted to the heart wall, and thus assist refilling either by means of a relative vacuum produced between the jacket and heart wall (following chest closure and removal and/or absorption of any air or free fluid) or by means of direct adhesion of the heart wall to the jacket during healing.
  • the jacket preferably has means provided for egress of tissue fluid that may accumulate, either discrete fenestrations [44] or porosity of at lease part of the structure.
  • the basal portion has either pre-cut apertures for the great vessels and atria or is suited for cutting these as required at operation.
  • dashed lines indicate sites of the aperture for the aorta [10] and of the aperture for the left atrium [8].
  • Figure 2 shows the same jacket in place on an intact heart in diastole. Those parts labeled in figure 1 are similarly labeled in figure 2. The left ventricle is obscured by the jacket in figure 2. The free-wall part of the jacket extends to the margins of the right ventricle [3]. The basal part surrounds the left atrium [4] and aorta [6], with the margins of this part extending between the left atrium [4] and right atrium [5] as well as between the aorta [6] and pulmonary artery [7].
  • Figure 3 shows the jacket in place on an intact heart in systole, parts are labeled the same as in figure 2.
  • the jacket may be, but is not necessarily, isotropic and/or homogeneous in structure.
  • the ventricular portion of the jacket is preferably not obstructive to through-flow of tissue fluid, allowing any such fluid accumulating near the heart to exit and thus be more likely to be reabsorbed.
  • the jacket may be fenestrated in multiple places as shown in figure 1 and figure 2 to allow egress of tissue fluid or the jacket may be diffusely porous to tissue fluid.
  • the jacket's flexural elasticity may be imposed by spring elements that make up part or all of its structure.
  • the spring elements are preferably metal that both is biologically minimally reactive and possesses a defined 'endurance limit/, meaning a level of tensile, compressive, or shear stress which may be repetitively imposed for an infinite number of cycles without fatigue failure.
  • Examples are commercially pure titanium, nickel-titanium alloy (Nitinol), and several types of stainless steel.
  • Figure 4 shows a preferred embodiment in which a serpentine pattern spring wire grid structure [45] is clad in polymeric padding [46], composed preferably of a polymer mesh [87], such as polyester, which is in turn impregnated with a soft elastomer [88] such as silicone rubber.
  • FIG. 5 A nonlimiting example of an alternate construction in which spring elements make up all of the jacket's structure is shown in figures 5 (close detail) and 6 (whole jacket for left ventricular application); the network of spring elements is generally finer than in embodiments in which a composite fabrication is used.
  • fine serpentine wire [47] is woven, knitted, braided or otherwise enmeshed, with or without local welding or adhesion into a jacket having a free-wall section [42] and a basal section [43], with the basal section have a left atrial and mitral aperture [8] and an aortic aperture [10].
  • the spring elements may alternatively be made of nonmetallic materials such as glass fibers, carbon fibers, composites of such fibers with matrix materials such as an epoxy or polyester compound, or other materials — either single composition or composite — with similar mechanical and biologic properties.
  • the spring elements may be of any configuration known to those familiar with mechanical design, such as ribbon, leaf, corrugated sheet, coil, bar, or serpentine wire, with present preference being serpentine wire.
  • Mechanical behavior of either the entire jacket or portions of it may be altered by design by varying the number of spring elements, joining techniques between spring elements, the distribution and orientation of spring elements, thickness or gauge of materials, and spring configuration at any site.
  • serpentine wire metal spring elements “configuration” in this context means periodicity of undulations, amplitude of undulations, and the pattern (that is, whether the pattern is sinusoidal, continuous link of circular arcs with or without straight segments, and so forth).
  • the jacket may be partially or totally constructed of soft materials, which contribute all, or part of its flexural elasticity.
  • soft materials may be polymer fibers (such as polyester) (either unorganized or organized in some fashion such as a braid, weave or knit).
  • these soft materials may be an elastomeric polymer (such as silicone rubber or a polyurethane).
  • the soft material may be a fiber structure such as described above, impregnated with an elastomeric polymer such as also described above, so as to form a fiber-reinforced, elastomeric- matrix composite.
  • the jacket may be comprised of multiple materials such as spring elements of the types described above in a network encased in soft materials such as the polymer fibers, the elastomeric polymer, or the composite of both described above.
  • a preferred embodiment of composition shown in a nonlimiting example in figure 12, employs titanium serpentine springs that are clad in polyester mesh and then vacuum impregnated with silicone rubber.
  • the jacket may have additional cushioning, such as a layer of very low durometer elastomer, over all or part of its inner surface At least part of the jacket's inner surface may be textured so as to encourage adhesion to the heart wall during healing. Regions of the inner surface may have additional cushioning or texturing or both or neither. Texturing with a material such as polyester velour, overlaying or incorporated in all or part of the jacket's inner surface, in intended to encourage secure adherence to heart surface during healing. This is shown in figure 7, including the textured area [48].
  • the jacket may have a smooth membrane, such as silicone or polyurethane, overlaying or incorporated in its inner surface to discourage tissue adhesion and encourage a thin, flexible, stable, and mobile fibrous encapsulation.
  • the needles of the completed circumferential row of sutures or cords, extending from bolsters, framework or other means of interventricular septum stabilization are, after exiting the ventricular or atrial external surfaces, advanced through the substance of the jacket near its margin, following by lowering the jacket into place and tying in a manner used by and familiar to cardiac surgeons for sewing and seating a prosthetic heart valve.
  • Protective structures, such as those described below, for the great vessel(s) and atrium(or atria) are placed prior to lowering the jacket into position and tying the sutures, which secure the jacket.
  • Figure 8 shows a left-side device jacket suspended above the heart while sutures exiting from internal septal-supporting components are placed circumferentially in the margins of the jacket, both its free-wall and its basal sections.
  • a repair patch [52] for atrial separation has been placed, repairing the medial wall defect in the right atrium after separation from the interatrial septum. This maneuver is required for the basal jacket margin to securely support the mitral annulus and/or, in a biventricular or right side device, the tricuspid valve.
  • the aortic sleeve [13] and the left atrial collar [49], both protective structures, have been placed (these are described in detail below).
  • Sutures [50] originating from the basal margin of the septal support components either those described in U.S.
  • margins are brought to rest between the separated atrium adjacent the tricuspid valve [28] and enclosing both the left atrium [4] mitral valve [15] as well as the aortic root [53]. At least most of the free wall of the left ventricle [2] is supported.
  • Figure 9 shows the jacket after it has been lowered into proper position and the sutures tied. Part numbers are the same as for Figure 8. Both of these illustrate a left-side only device, as a nonlimiting example. The procedure for a right-side only is analogous in each step, whereas in a bilateral device all components except the right free-wall section are placed in a procedure identical to that illustrated (noting that the basal section will in that event extend over the whole base, including the right atrium and pulmonary artery root); right free wall section components are subsequently attached to the left free wall section.
  • the sutures are mechanically fixed, rather than tied, to prepared receiving elements in the jacket near its margins.
  • An indicator device may be used with, calibrating tightness of tied sutures joining internal structures, such as bolsters or frame struts, through myocardium to jacket.
  • the indicator device may function as a surface tension indicator to allow control of suture tying tightness in which a laminated structure, with alternate laminae translucent and either textured or colored, in such a way that a visible change signals achievement of adequate tightness for control of bleeding.
  • This indicator system may be constructed in such a way that a visible change signals achievement of excessive tightness that, if not reversed, could risk tissue damage.
  • a specific example of such a system follows, as illustrated in figures 10a, 10b, and 10c.
  • the jacket may be equipped on part or all of its outer surface with a translucent layered composition structured so that tying of a penetrating suture [30] results in a local color or other visible change that is at least semi quantitatively related to the tightness of tying and thus to the compressive stress being imposed on the underlying heart surface.
  • a translucent layered composition structured so that tying of a penetrating suture [30] results in a local color or other visible change that is at least semi quantitatively related to the tightness of tying and thus to the compressive stress being imposed on the underlying heart surface.
  • a nonlimiting example is a laminar structure in which the first, third, and fifth layers [parts 54, 56, and 58] are transparent and either colored yellow, blue, and red, respectively, or having none, left-to-right cross-hatches, and up-to- down crosshatches, respectively, with the first layer [54] being the outer surface.
  • each of these layers are of a thin elastomer with the appropriate pigment or pattern added, and preferably reinforced with a fine polymer fiber mesh to enhance tear resistance.
  • the second layer [part 55] is a very thin layer of extremely low durometer (e.g., an order of magnitude softer than the pigmented or cross-hatched layers) clear elastomer
  • the fourth layer [part 57] is similar to the second layer except either for being thicker, firmer, or both — and thus less easily compressed.
  • the second and fourth may contain suspended colloidal particles or gas bubbles so as to increase light diffusion and thus decrease transparency when not substantially compressed. This structure will provide an indicator of the compressive force of a tied penetrating suture loop.
  • the mechanism is that a certain degree of compressive stress will cause sufficient thinning of the second layer that the initially visible yellow surface color becomes green as it becomes compressed against the blue layer, and then brownish gray as the three indicating layers (the first, third, and fifth) are all closely compressed by the thinning of the second and fourth layers.
  • thinning of the second layer with pressure causes the non-lined appearance of the first to transform locally to the left-to-right crosshatching as the third layer becomes visible through it, and by a similar process at still higher tying pressure then transforms to a grid pattern as the fifth layer also becomes visible from the surface in the immediate vicinity of the suture being tightened.
  • any excessively compressed region [8] will be readily recognizable.
  • construction parameters may be selected such that the yellow to green (or clear to lined) transition occurs at a compressive stress which in the underlying tissue is expected to arrest bleeding, while the green to brownish- gray (or lined to gridded) occurs at a stress somewhat lower than one at which tissue ischemia is risked. This may be calibrated based on experimental assessment to a level where tying 'tight enough but not too tight' is readily achieved by visual guidance.
  • Figure 10a is an 'exploded' view of laminar construction as described in the prior paragraph.
  • Figure 10b illustrates the first transition where single direction cross hatch marks are visible, representing achievement of the 'safe and necessary' pressure, whereas the grid cross hatching in figure 10c indicates the point of excessive compressive stress — suggesting the suture be loosened.
  • An alternative means of calibrating suture tying tightness while securing the jacket [61] is the tensile elastic element such as a spring of various configurations or a loop [62] of elastomeric polymer such as shown in the nonlimiting example of figure 11a and b.
  • the tensile elastic element such as a spring of various configurations or a loop [62] of elastomeric polymer such as shown in the nonlimiting example of figure 11a and b.
  • This is complemented with visible indicators of the elastic element's extension, and thus tension placed upon it. These indicators may be ridges, grooves, color bands, dashes [63] or other marks and may be labeled with numbers, letters, and so forth. Special markings such as the 'O's' [64] may indicate inadequate tension and the 'X's' [65](both in figure 11a) may indicate excessive tension.
  • the tensile elastic element is based at a short distance from the site of suture penetration and looped by the penetrating suture ends before tying. Deformation may be gauged by marks on the jacket surface to be too loose, as the beginning knot [66] in figure 11a or in a range deemed safe as is the knot in figure 11 b [67] and the knot completed.
  • the established position may be made permanent by any commonly used fixation technique such as another suture, a staple, or a brad, or a combination of these or other techniques and devices to anchor the tied cord or suture to the substance of the jacket at the determined location.
  • a tension-calibrating device for fixing sutures which is an adaptation of ratcheted tension-control fastening devices familiar to those in both cardiac surgery and engineering design (e.g. 'snap-band guns') configured to work with sutures after penetrating from bolsters and regulate tension at which sutures are mechanically fixed.
  • ratcheting and tension limiting features of such devices may be either adapted and incorporated into prefixed openings in the margins of (the jacket into which the sutures may be inserted or configured to be used with sutures penetrating the jacket's substance by needles or by other means.
  • An auxiliary structure may be required for stabilization and protection of great vessel origins during and after placement of the jacket. These structures may or may not provide for fixation to the jacket, to the great vessel or to both.
  • a 'sleeve' may be configured for fitting around the base or root of the aorta or pulmonary artery, the sleeve and the vessel which it surrounds being within that vessel's aperture in the basal portion of the active jacket.
  • the sleeve is illustrated in figures 12 and 13.
  • the sleeve may have a tubular portion [68] that envelopes the aorta or pulmonary artery for approximately 5 to 40 mm starting near the level of the valve commisures, to be placed after separation of the soft tissue joining the pulmonary artery and aorta.
  • the tubular portion of the sleeve may be of a biocompatible material, that is porous such as expanded polytetraflurethylene (ePTFE) or knitted or woven polyester.
  • the tubular portion of the sleeve may be of a biocompatible material that is nonporous such as solution cast polyurethane.
  • the tubular portion the sleeve may be complete with intent to place over the proximal part of a transected great artery in the case of a complete or partial autotransplantation placement technique.
  • the tubular portion of the sleeve may be separated vertically at one point on the circumference, preferably at the point that will be over the center of the noncoronary cusp of the aortic valve in the case of aortic use.
  • the sleeve may have a flared portion [69] that extends outward between the great vessel and the part of the jacket that is adjacent the great vessel aperture.
  • the junction of the tubular and flared portions of the sleeve may be smooth and continuous to conform to the underlying tissue surface.
  • the flared portion of the sleeve [69] may be of a biocompatible material that is in two layers joined at the margins, both porous, such as expanded polytetraflurethylene (ePTFE) or knitted or woven polyester, with solid particles, spherical or otherwise, 1 to 5 mm in diameter, loosely packed between the layers in the fashion of a 'bean bag' [70] so that it will protect the base of the great vessel against potential abrasion by the margins [71] of the active jacket's great vessel aperture(s).
  • ePTFE expanded polytetraflurethylene
  • the flared portion of the sleeve may be composed of a biocompatible material that is in two layers joined at the margins, both nonporous, such as solution cast polyurethane, possibly reinforced with another polymer membrane, with-a liquid (such as saline solution or silicone oil) or a gel (such as silicone gel or a biocompatible hydrogel) contained between the layers
  • the flared portion of the sleeve may be composed of a biocompatible material that is in two layers joined at the margins, both being asymmetric in the case of the aorta, extending outward in a lobular fashion over the location of the origin of the two main coronary arteries and their more proximal branches in order to protect them from any eroding effect of the margins of the aperture.
  • An auxiliary structure may be required for stabilization and protection of atrial bases including atrioventricular valve annuli during and after placement of the jacket. These structures may or may not provide for fixation to the jacket, to the atrium, or to both.
  • a structure termed a 'collar' is taught.
  • a method for preparing the atria for collar placement consists of incising the right atrial wall adjacent the intra-atrial septum and then repairing the resulting defect in the medial right atrial wall with a patch of any material, autologous or prosthetic, which is commonly used for septal defect repair, as illustrated in figure 15.
  • the right atrial wall is incised at its junction with the atrial septum, ideally from an extracardiac approach after full dissection through the interatrial fat pad.
  • the incision is carried to the tricuspid annulus anteriorly and posteriorly.
  • the lower margin of a patch [52] of the material selected is then sewn, everted, with mattress sutures to the tricuspid annulus, protecting the septal leaflet of the tricuspid valve [28], and to the base of right atrial side of the previous interatrial septum (which is now the medial wall of the left atrium for a 3 to 5 mm wide broad attachment.
  • the margins are then attached, by, for example, a suture line [73] to the remainder of the right atrial defect.
  • the everted lower lip of the patch provides space in which the margin of the active jacket [71] may rest, with optional separation and reattachment of that margin if the procedure is done on an intact heart [90].
  • the separation point in not required, since the intact basal section of the jacket can simply be positioned on the heart before reanastamosis with the posterior atrial margins.
  • a collar is configured for fitting around the base of the left or of the right atrium, the collar and the atrium which it surrounds being positioned within that atrium's aperture in the basal portion of the active jacket described above.
  • the collar is illustrated in figures 16 and 17.
  • the collar is made of a flexible thin material having a defined stiffness (i.e., neither flaccid nor rigid), for example a composite of polyester fiber that is knitted or woven or otherwise organized and vacuum impregnated with an elastomer such as low durometer silicone rubber.
  • the collar has a short tubular portion [76] approximately 3 to 10 mm long.
  • the collar has a 'shingle' portion [77], which is smoothly continuous with those parts of the tubular portion exclusive of the prior junction with the contralateral atrium and the region of the great vessel sleeve, and extending outward over the epicardium of the atrioventricular groove, the vessels contained within the fat over the atrioventricular groove, and the adjacent ventricular surface.
  • the shingle protects the right coronary artery and vein; on the left it protects the circumflex artery [78], the coronary sinus [79] and the adjacent portion of the left ventricular free wall [80].
  • the left atrial wall [81] flares out above the tubular portion's free margin.
  • the method of placing the collar is as follows: An annuloplasty ring [31], of standard rigid, semirigid, or flexible type, is fixed onto the mitral annulus using standard operative technique to assure adequate apposition of the posterior leaflet [82] and anterior leaflet [83] of the mitral valve [15]. Then the collar is either slipped over the atrial base intact, in the event of a cardiectomy/ autotransplant technique, or separated and reattached in the event of an in situ heart technique. Sutures [84] are placed from the annuloplasty ring through the proximal atrial wall to the collar.
  • each of those components might be coupled together.
  • they could be integrally fabricated such that a single structure includes the jacket, the great vessel sleeve, and the atrial incorporated all incorporated in a single element.
  • the individual elements might be interlocked such as with interlocking surfaces.
  • mating hook and loop fastening surfaces might be utilized on the heart-facing surface of the jacket for a short distance (a few millimeters) adjacent the aortic aperture and on the away-from-the-heart surface on the flared portion of the aortic sleeve.

Landscapes

  • Health & Medical Sciences (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic 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

L'invention concerne un coussin ou une gaine active amortie à déformation cyclique (39) qui entoure la surface extérieure ou la surface épicardique d'au moins une chambre (2, 3, 4, 5) du coeur naturel, y compris de sa base. Cette gaine est conçue de sorte que des composants internes peuvent être suspendus à la gaine (39) par des cordons qui pénètrent dans la paroi du coeur afin de compléter un harnais de contention sur toute la limite tridimensionnelle de la chambre ou des chambres. Le coussin ou la gaine (39) crée des ouvertures de protection et de stabilisation (8, 9, 10) pour les oreillettes et leurs valves d'entrée ainsi que pour les vaisseaux importants et leurs valves de sortie. Le coussin ou la gaine (39) est équipé d'un ou plusieurs mécanismes d'activation (37, 38) qui changent cycliquement de forme sur un ou plusieurs sites, modifiant ainsi la forme de la paroi du coeur et le volume de la chambre.
PCT/US2004/018298 2002-07-18 2004-06-09 Gaine deformante pour un dispositif d'activation cardiaque Ceased WO2004110307A2 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
EP04754797A EP1631348A4 (fr) 2003-06-09 2004-06-09 Gaine deformante pour un dispositif d'activation cardiaque
US11/298,428 US7850729B2 (en) 2002-07-18 2005-12-08 Deforming jacket for a heart actuation device

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US47708603P 2003-06-09 2003-06-09
US60/477,086 2003-06-09

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US10/667,877 Continuation-In-Part US20040059180A1 (en) 2002-07-18 2003-09-22 Basal mounting cushion frame component to facilitate extrinsic heart wall actuation

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US11/298,428 Continuation US7850729B2 (en) 2002-07-18 2005-12-08 Deforming jacket for a heart actuation device

Publications (2)

Publication Number Publication Date
WO2004110307A2 true WO2004110307A2 (fr) 2004-12-23
WO2004110307A3 WO2004110307A3 (fr) 2005-03-10

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PCT/US2004/018298 Ceased WO2004110307A2 (fr) 2002-07-18 2004-06-09 Gaine deformante pour un dispositif d'activation cardiaque

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EP (1) EP1631348A4 (fr)
WO (1) WO2004110307A2 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8019404B2 (en) 2006-10-06 2011-09-13 The Cleveland Clinic Foundation Apparatus and method for targeting a body tissue
US8694077B2 (en) 2006-10-06 2014-04-08 The Cleveland Clinic Foundation Apparatus and method for targeting a body tissue
US9492623B2 (en) 2006-10-06 2016-11-15 The Cleveland Clinic Foundation Apparatus and method for targeting a body tissue
US9492270B2 (en) 2007-09-12 2016-11-15 Alan Joel Melvin Medical device and tension member for use in a subject

Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20020007216A1 (en) 1996-01-02 2002-01-17 Melvin David Boyd Heart wall actuation device for the natural heart

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5383840A (en) * 1992-07-28 1995-01-24 Vascor, Inc. Biocompatible ventricular assist and arrhythmia control device including cardiac compression band-stay-pad assembly
CA2402504A1 (fr) * 2000-03-10 2001-09-20 Paracor Surgical, Inc. Harnais cardiaque extensible permettant de traiter l'insuffisance cardiaque congestive

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20020007216A1 (en) 1996-01-02 2002-01-17 Melvin David Boyd Heart wall actuation device for the natural heart

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP1631348A4

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8019404B2 (en) 2006-10-06 2011-09-13 The Cleveland Clinic Foundation Apparatus and method for targeting a body tissue
US8694077B2 (en) 2006-10-06 2014-04-08 The Cleveland Clinic Foundation Apparatus and method for targeting a body tissue
US9492623B2 (en) 2006-10-06 2016-11-15 The Cleveland Clinic Foundation Apparatus and method for targeting a body tissue
US9498584B2 (en) 2006-10-06 2016-11-22 The Cleveland Clinic Foundation Apparatus and method for targeting a body tissue
US9498585B2 (en) 2006-10-06 2016-11-22 The Cleveland Clinic Foundation Apparatus and method for targeting a body tissue
US9492270B2 (en) 2007-09-12 2016-11-15 Alan Joel Melvin Medical device and tension member for use in a subject

Also Published As

Publication number Publication date
EP1631348A2 (fr) 2006-03-08
EP1631348A4 (fr) 2008-12-24
WO2004110307A3 (fr) 2005-03-10

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