Source: http://www.google.com/patents/US7871369?dq=6011510
Timestamp: 2017-10-24 04:33:48
Document Index: 47485890

Matched Legal Cases: ['art.\n12', 'art 102', 'art 102', 'art 102', 'art 102', 'art 102', 'art 102']

Patent US7871369 - Cardiac sleeve apparatus, system and method of use - Google Patents
Cardiac assist sleeve and methods for using and making the cardiac assist sleeve that includes first elongate strips and second elongate strips of memory alloy that change shape to change a volume of cardiac assist sleeve....http://www.google.com/patents/US7871369?utm_source=gb-gplus-sharePatent US7871369 - Cardiac sleeve apparatus, system and method of use
Publication number US7871369 B2
Application number US 12/415,583
Also published as US7524282, US20070049789, US20090187064, WO2007027597A1
Publication number 12415583, 415583, US 7871369 B2, US 7871369B2, US-B2-7871369, US7871369 B2, US7871369B2
Inventors Robert M. Abrams
Patent Citations (207), Non-Patent Citations (7), Referenced by (1), Classifications (5), Legal Events (3)
Cardiac sleeve apparatus, system and method of use
US 7871369 B2
Cardiac assist sleeve and methods for using and making the cardiac assist sleeve that includes first elongate strips and second elongate strips of memory alloy that change shape to change a volume of cardiac assist sleeve.
1. A method of forming a cardiac assist sleeve, comprising:
arranging first elongate strips of a first shape-memory alloy, the first elongate strips having a cross-sectional shape taken perpendicularly across a lengthwise line of symmetry;
arranging second elongate strips of a second shape-memory alloy to intersect and pass the first elongate strips, where the first elongate strips and the second elongate strips define a volume that changes as the cross-sectional shape of the first elongate strips reversibly change between a first cross-sectional shape having flat surfaces and a second cross-sectional shape having one convex surface and one concave surface opposite the convex surface to change the volume of the cardiac assist sleeve; and
securing a first end of the first elongate strips around a collar.
2. The method of claim 1, including forming the first elongate strips and the second elongate strips in a sputter coating operation.
3. The method of claim 2, including cladding a third shape memory alloy to the first elongate strips and the second elongate strips.
4. The method of claim 3, including depositing an electrically insulating layer between the first shape-memory alloy and the third shape-memory alloy.
5. The method of claim 1, including imparting a first shape into the first shape-memory alloy of the first elongate strips.
6. The method of claim 1, including imparting a second shape into the second shape-memory alloy of the second elongate strips.
7. The method of claim 1, including joining a second end of the first elongate strips at a common location.
8. The method of claim 1, where arranging the second elongate strips to intersect and pass the first elongate strips includes weaving the first elongate strips and the second elongate strips.
9. A method of using a cardiac assistance device, comprising:
positioning a cardiac assist sleeve adjacent a left ventricle of a heart, where the cardiac assist sleeve includes:
first elongate strips of a first shape-memory alloy, the first elongate strips having a cross-sectional shape taken perpendicularly across a lengthwise line of symmetry; and
second elongate strips of a second shape-memory alloy that intersect and pass the first elongate strips, the first elongate strips and the second elongate strips define a volume to receive the left ventricle of the heart;
securing a portion of the cardiac assist sleeve to the heart; and
assisting the left ventricle of the heart by reversibly changing the cross-sectional shape of at least one of the first elongate strips between a first cross-sectional shape having perpendicular sides and a second cross-sectional shape having one convex surface and on concave surface opposite the convex surface to change the volume of the cardiac assist sleeve.
10. The method of claim 9, where producing reversible changes in the cross-sectional shape includes applying an electrical potential across the first shape-memory alloy and the second shape-memory alloy to produce the changes in the cross-sectional shape.
11. The method of claim 10, where applying the electrical potential is synchronized with predetermined portions of a contraction cycle of the heart.
12. The method of claim 9, where securing a portion of the cardiac assist sleeve to the heart includes wrapping the cardiac assist sleeve around at least a portion of the heart, where at least a portion of the cardiac assist sleeve freely overlaps adjacent the portion of the cardiac assist sleeve secured to the heart.
This application is a continuation of U.S. application Ser. No. 11/215,666 filed Aug. 29, 2005, the specification of which is incorporated herein by reference.
Congestive heart failure is a progressive and debilitating illness. The disease is characterized by a progressive enlargement of the heart. As the heart enlarges, it is required to perform an increasing amount of work in order to pump blood with each heartbeat. In time, the heart becomes so enlarged that it cannot adequately supply blood. An afflicted patient is fatigued, unable to perform even simple exerting tasks, and experiences pain and discomfort.
Patients suffering from congestive heart failure are commonly grouped into four classes (i.e., Classes I, II, III and IV). In the early stages (e.g., Classes I and II), drug therapy is the most commonly prescribed treatment. Drug therapy treats the symptoms of the disease and may slow the progression of the disease. Unfortunately, there is presently no cure for congestive heart failure. Even with drug therapy, the disease will progress.
One treatment for late-stage congestive heart failure is heart transplant. However, even if the patient qualifies for transplant and a heart is available for transplant, it is noted that heart transplant procedures are very risky, invasive, expensive and only shortly extend a patient's life. For example, prior to transplant, a Class IV patient may have a life expectancy of 6 months to one-year. Heart transplant may improve the expectancy to about five years. Similar risks and difficulties exist for mechanical heart transplants as well.
Another technique for the treatment for late stage congestive heart failure is a cardiomyoplasty procedure. In this procedure, the latissimus dorsi muscle (taken from the patient's shoulder) is wrapped around the heart and electrically paced synchronously with ventricular systole. Pacing of the muscle results in muscle contraction to assist the contraction of the heart during systole. However, even though cardiomyoplasty has demonstrated symptomatic improvement, studies suggest the procedure only minimally improves cardiac performance. Moreover, the procedure is highly invasive, expensive and complex, requiring harvesting a patient's muscle and an open chest approach (i.e., sternotomy) to access the heart.
Recently, a surgical procedure referred to as the Batista procedure has been developed. The procedure includes dissecting and removing portions of the heart in order to reduce heart volume. Others have used external constraints such as jackets, girdles, fabric slings or clamps to constrain and remodel the heart and reduce heart volume. See, e.g., U.S. Pat. No. 6,293,906 (citing numerous references including U.S. Pat. Nos. 5,702,343 and 5,800,528) and U.S. Pat. No. 6,095,968. In accordance with an example from the above '906 patent, a cardiac constraint device can be placed on an enlarged heart and fitted snug during diastole; for example, a knit jacket device can be loosely slipped on the heart, the material of the jacket can be gathered to adjust the device to a desired tension, and the gathered material can be sutured or otherwise fixed to maintain the tensioning.
FIG. 1 illustrates an embodiment of a cardiac assist sleeve according to the present invention.
FIGS. 2A and 2B illustrate one embodiment of a segment of the cardiac assist sleeve according to the present invention.
FIGS. 3A and 3B illustrate one embodiment of a segment of the cardiac assist sleeve according to the present invention.
FIGS. 4A and 4B illustrate one embodiment of a segment of the cardiac assist sleeve according to the present invention.
FIGS. 5A and 5B illustrate embodiments of a strip of the cardiac assist sleeve according to the present invention.
FIGS. 6A and 6B illustrate one embodiment of a strip of the cardiac assist sleeve according to the present invention.
FIG. 7 illustrates an embodiment of a cardiac assist sleeve according to the present invention.
Embodiments of the present invention are directed to an apparatus, system, and method for treating congestive heart failure. In addition, the embodiments of the present invention can be used in treating patients who have had an acute myocardial infarction, in addition to other causes of left ventricular failure from other diseases such as idiopathic dilated cardiomyopathy, hypertrophic cardiomyopathy, and viral cardiomyopathy.
Embodiments of the present invention include a cardiac assist sleeve that acts to apply elastic compressive reinforcement on the ventricles of the heart. Application of the elastic compressive reinforcement is believed to help reduce tension on the ventricle walls and to assist in the pumping action of the left ventricle. In addition, embodiments discussed herein allow for compressive reinforcement to be applied to the left ventricle without unduly limiting the natural volumetric changes of the left ventricle (e.g., without limiting the natural diastolic volume of the left ventricle).
FIG. 1 illustrates one embodiment of a cardiac assist sleeve 100 positioned over a portion of a heart 102. As illustrated, the cardiac assist sleeve 100 includes first elongate strips 104 that extend substantially in a first direction 106, and second elongate strips 108 that extend in a second direction 110. As used herein, an “elongate strips” includes elongate structures having a polygonal cross-section having perpendicular sides, one or more convex sides, or one or more concave sides. These embodiments, however, are not limited to the present examples as other cross-sectional geometries are also possible. An example can include, but is not limited to, structures having a rectangular cross-section. In addition, such structures need not have a uniform width. In other words, dimensions of the polygonal cross-section can change along the length of one or more of the elongate strips.
The first elongate strips 104 and the second elongate strips 108 of the cardiac assist sleeve 100 are configured to define a volume into which at least a portion of the heart 102 resides. As illustrated, the volume of the cardiac assist sleeve 100 can encompass a volume from approximately the A-V groove to the apex of the left ventricle. The volume of the cardiac assist sleeve 100 reversibly changes during the cardiac cycle of the heart 102 to apply elastic compressive reinforcement on the ventricles of the heart 102. In one embodiment, this change in volume is imparted to the cardiac assist sleeve 100 due to the configuration and the materials used in the first elongate strips 104 and the second elongate strips 108 of the cardiac assist sleeve 100.
In one embodiment, the first elongate strips 104 are formed of a first shape-memory alloy and the second elongate strips 108 are formed of a second shape-memory alloy. As used herein, a “shape-memory alloy” includes those metals that have a predetermined geometry (i.e., shape) to which the structure made from the metal returns after being elastically deformed. The shape memory alloys can include, but are not limited to, those that return to its predetermined geometry due to thermal energy (i.e., temperature), such as Nitinol, and/or the influence of a magnetic field. Other examples of shape memory alloys include those composed of titanium-palladuim-nickel, nickel-titanium-copper, gold-cadmium, iron-zinc-copper-aluminum, titanium-niobium-aluminum, hafnium-titanium-nickel, iron-manganese-silicon, nickel-titanium, nickel-iron-zinc-aluminum, copper-aluminum-iron, titanium-niobium, zirconium-copper-zinc, and nickel-zirconium-titanium. Other metal and metal alloys are also possible.
As illustrated, the second elongate strips 108 intersect and pass the first elongate strips 104 in the second direction. The first and second elongate strips 104 and 108 can include individual elongate strips that are associated with each other so as to form the cardiac assist sleeve 100. Alternatively, the first and second elongate strips 104 and 108 can be formed from one or more sheets of the shape memory alloy that are processed to provide the strips 104 and 108. In one embodiment, the first elongate strips and the second elongate strips have a thickness of 10 to 200 microns.
For example, individual elongate strips can be shaped (e.g., cut), arranged, and joined to form the cardiac assist sleeve 100. Shaping of the individual elongate strips can be accomplished by laser cutting, water jet cutting, electron discharge machine, and/or other cutting methods as are known or will be known.
The strips can then be arranged on a template (e.g., a model) of a heart. In one embodiment, the template can be of the patient's heart that is to receive the resulting cardiac assist sleeve 100.
The elongate strips can then be joined at one or more predetermined locations through chemical and/or mechanical joining. For example, predetermined locations of the elongate strips can be bonded to each other through the use of adhesives (e.g., chemical adhesives) and/or laser welding. Other joining techniques are also possible. As will be appreciated, the strips need not be secured and/or joined at every location where they intersect.
In an alternative embodiment, the strips 104 and 108 of the cardiac assist sleeve 100 can be formed from one or more sheets of the shape memory alloy. As used herein, a sheet of the shape memory alloy can include those formed from calendaring techniques, film forming techniques (e.g., photochemical etching), or sputter coating techniques. For example, the strips 104 and 108 can be formed as a thin film in a sputter coating process. A useful sputter coating process can include those described in U.S. Pat. No. 6,533,905 to Johnson et al. entitled “Method for Sputtering TiNi Shape-Memory Alloys,” which is incorporated herein by reference in its entirety.
The shape memory alloy noted herein may be used in conjunction with radioopaque filler materials such as barium sulfate, bismuth trioxide, bismuth carbonate, powdered tungsten, powdered tantalum, or the like so that the location of the sleeve 100 may be radiographically visualized within the human body. In addition, therapeutic agent(s) can be applied to the surfaces of the strips 104 and 108. The variety of different therapeutic agents that can be used include, without limitation: antiinfectives such as antibiotics and antiviral agents; analgesics and analgesic combinations; anti-inflammatory agents; hormones such as steroids; and naturally derived or genetically engineered proteins, polysaccharides, glycoproteins, or lipoproteins, anti-thrombotic agents, anti Pt agents, anti-immunogenic agents, anti-mitotic agents, anti proliferative agents, and angiogenic agents.
As discussed herein, the volume of the cardiac assist sleeve 100 changes during the cardiac cycle of the heart 102 to apply elastic compressive reinforcement on the ventricles of the heart 102. In one embodiment this change in volume results from reversible changes in the shape of at least one of the first elongate strips 104 and/or the second elongate strips 108.
Examples of changes to the first and second elongate strips are illustrated in FIGS. 2A-2B and 3A-3B. FIGS. 2A and 2B illustrate segments of the first and second elongate strips 204 and 208 in which the first elongate strips 204 change shape to reversibly change the volume of the cardiac assist sleeve. As illustrated, the first elongate strips 204 include a cross-sectional shape across the first direction that reversibly changes between a flat cross-sectional shape and a curved cross-sectional shape to change the volume of the cardiac assist sleeve.
In one embodiment, the length of strips 208 do not significantly change, so as strips 204 curve, they reduce the volume of the sleeve. As the heart fills during diastole the curves in strips 204 are elastically deformed (i.e., compressed so as to flattened) to look like those in FIG. 2A. Elasticity refers to the ability of a material or object to deform and recover its shape when a load is first applied and then removed. In its deformed state, the strips 204 can store potential energy that is released as the heart starts into systole. Strips 204 would have to attach (if at all) to strips 208 so as to not constrain the curving of strips 204. For example, strips 204 could be attached at its outer edge to strips 208.
As will be appreciated, the number of curves (density), their shape (e.g., U-shaped, V-shaped, teardrop-shaped, keyhole-shaped), direction, material dimensions (e.g., thickness) of the strip 204 can be varied to modify the stiffness and the elasticity of the sleeve 200. In addition, it is possible to modify one or more of these variables on one or more of the strips to provide selective elastic resistance (e.g., stiffness) in different areas of the sleeve 200. For example, it would be possible to make the sleeve 200 stiffer in the area surrounding the left ventricle as compared to the area surrounding the right ventricle.
FIGS. 3A and 3B provide an additional embodiment of changes that can occur to the first and second elongate strips so as to change volume of the sleeve. In the present example, both the strips 204 and 208 can change shape to provide reversible changes to the volume of the sleeve. In FIG. 3A, the strips 304 can change shape as discussed herein with respect to FIGS. 2A and 2B. The second elongate strips 308 include a cross-sectional shape taken along the second direction that reversibly changes between a flat cross-sectional shape (illustrated in FIG. 3A) and a non-flat cross-sectional shape (illustrated in FIG. 3B) to change the volume of the cardiac assist sleeve.
As illustrated, the second elongate strips 308 can have a curving (e.g., sinusoidal shape) geometric shape along the second direction. As the heart fills during diastole the curves in 304 and 308 are compressed (flattened) to look like those in 3A. There is potential energy stored in the flattened strips 304 and 308 that is released as the heart starts into systole. Strips 304 would have to attach (if at all) to strips 308 so as to not constrain the curving of strips 304 and 308. For example, strips 304 can be attached at their outer edge to strips 308. Alternatively, strips can be attached along their face, where the curves in strips 304 and 308 are configured to bend in the same direction and to the same extent (the bends in each mirror each other).
The configurations of the strips in the sleeve also allow for volume changes to occur primarily circumferentially around the left ventricle of the heart as apposed to linearly along the central axis of the left ventricle. In one embodiment, this is because changes to the shape of the first strips occur to the cross-sectional shape of the strips, where as changes to the shape of the second strips occur to the elongate shape of the strips.
Referring again to FIG. 1, each of the first elongate strips 104 includes a first end 112 and a second end 114. In one embodiment, the first end 112 of the strips 104 are joined at a collar 116. In one embodiment, the collar is where the ends of strips 104 are joined at set locations. Set locations can be radially symmetrical (e.g., equally spaced) around an axis extending in the first direction, but do not have to be. Collar could also include anchors (e.g., staples) or locations for sutures to be used to secure the sleeve to the heart. Two or more of the second ends 114 can further be joined at a common location. In one embodiment, this allows the relative positions of the first elongate strips 104 to be maintained.
As will be appreciated, the strips 104 and 108 can intersect and pass each other in a number of different configurations. For example, as illustrated in FIGS. 4A and 4B, the strips 404 and 408 can have a woven configuration. As illustrated in FIG. 4A, each of the first strip 404 and the second strip 408 alternate passing over and then under each other (e.g., a basket weave pattern). As illustrated in FIG. 4B, the first strips 404 can pass over and then under each of the second strips 408. Other weaving patterns are possible, including braiding of the first and second strips.
Strips can also be actuated when a potential and/or heat is applied to the strip. For example, when electrical potential or heat is applied to the strip in the stressed state (compressed states as illustrated in FIGS. 2A and 3A), the resistive force generated by the bending deformation increases. In essence, the strip can generate a contractile force when potential is applied to the strip. So, it is possible to actively power an otherwise passive elastic strip in order to achieve systolic pumping assistance.
Strips can also have a laminate structure that allows at least one layer of the strip to be actuated when an electrical potential and/or beat is applied to the strip. For example, first elongate strips can include a cladding of the first shape-memory alloy and a third shape-memory alloy, the first shape-memory alloy and the third shape-memory alloy each having at least one layer that extends in the first direction. In one embodiment, the first and third memory metal can be Nitinol that has had their respective geometries set at different temperatures.
As will be appreciated, elastically deforming the strips can provide for the actuator design that employs at least a bi-metal sandwich technology such that a spring element is biased against a contractile one-way shape memory effect of the memory metal (e.g., nitinol). This allows the strips to restore more fully to full strain recovery after each cycle.
In the present example, the first shape-memory alloy of the cladding can be actuated by the application of the electrical potential and/or heat to change its shape. This feature could be combined with the third shape-memory alloy that is conditioned to bend in the opposing direction of the first shape-memory alloy of the cladding to allow for work to be acquired from the strip as is moves through its full range of motion.
FIGS. 5A and 5B provide an illustration of a first strip 504 having the cladding (i.e., a sandwich) construction. As illustrated, first strip 504 includes a first layer 520 of the first shape-memory alloy and a second layer 522 of the third shape-memory alloy. FIG. 5B provides an illustration where a thermal and/or electrically insulating layer 524 is provided between layers 520 and 522. As will be appreciated, this same structure for the first strip 504 can be applied to the second strip discussed herein.
FIGS. 6A and 6B illustrate an embodiment in which a potential is applied to strip 604 having layers 620 and 622. FIG. 6A has layer 620 in its set geometric shape, whereas layer 622 is under tension. When electrical potential or heat is applied to layer 622 it is actuated to bend as illustrated in FIG. 6B. Upon bending, layer 620, acting as a spring element, deviates from its set geometric shape. When the potential is removed, the tension load in layer 620 returns the strip 604 to is configuration in FIG. 6A. This allows for work to be done in both directions as the strip 604 moves. So, a sleeve made with this strip configuration (when properly coupled to the heart) can provide assistance to the heart in both diastole and systole.
The sleeve illustrated in the present embodiments not only has the capability of acting as a passive restraint around the heart, but may also be actively powered to provide contractile assistance during systole and/or diastole. This may be done by the application of electrical potential to the sleeve.
FIG. 7 provides an illustration in which the sleeve 700 is coupled to leads 726 and 728 and a potential generator 730. Potential generator 730 includes a battery and circuitry for sensing portions of the cardiac cycle so as to more properly time the contractile assistance and to communicate via wireless (e.g., RF) with an external programmer 732.
The entire sleeve 700 can be configured to be actuated by the potential generator 730, and/or select portions of the sleeve 700. For example, in one embodiment just the first strips can be actuated during systole. Other combinations can be envisioned.
In another embodiment, the potential generator 730 can be used to modify the compliance/stiffness of the strips by applying different levels of electrical potential. As such, the potential is not used to actively “squeeze” the heart during systole, but rather to provide for adjustable compliance of the sleeve. This allows for adjustments in the amount of resistive pressure the sleeve exerts on the left ventricle during both systole and diastole. The passive stiffness of the sleeve can be set to change throughout the cardiac cycle, or it can be adjusted to maintain constant levels.
As will be appreciated, the sleeve 700 may be integrated with an implantable pacemaker or an internal cardiac defibrillator, according to the needs of the patient.
In addition, embodiments of the sleeve can also be utilized inside the LV chamber.
In one embodiment, the sleeve can be delivered through conventional cardiothoracic surgical techniques through a median sternotomy. Alternatively, the sleeve can be delivered through minimally invasive surgical access to the thoracic cavity. Such a minimally invasive procedure can be accomplished on a beating heart, without the use of cardiopulmonary bypass. Access to the heart can be created with conventional surgical approaches.
US5409460 Apr 15, 1993 Apr 25, 1995 The Beta Group Inc. Intra-luminal expander assembly
US6106473 Nov 6, 1997 Aug 22, 2000 Sts Biopolymers, Inc. Echogenic coatings
US6159142 Nov 5, 1998 Dec 12, 2000 Inflow Dynamics, Inc. Stent with radioactive coating for treating blood vessels to prevent restenosis
US6159237 Nov 5, 1998 Dec 12, 2000 Inflow Dynamics, Inc. Implantable vascular and endoluminal stents
US6304769 Oct 16, 1997 Oct 16, 2001 The Regents Of The University Of California Magnetically directable remote guidance systems, and methods of use thereof
US6398805 Apr 7, 2000 Jun 4, 2002 Inflow Dynamics Inc. Balloon expandable stent with low surface friction
US6416540 Nov 1, 2000 Jul 9, 2002 Sandip V. Mathur Magnetically actuated cleanable stent and method
US6478815 Sep 18, 2000 Nov 12, 2002 Inflow Dynamics Inc. Vascular and endoluminal stents
US6511325 May 4, 1998 Jan 28, 2003 Advanced Research & Technology Institute Aortic stent-graft calibration and training model
US6574497 Dec 22, 2000 Jun 3, 2003 Advanced Cardiovascular Systems, Inc. MRI medical device markers utilizing fluorine-19
US6663570 Feb 27, 2002 Dec 16, 2003 Volcano Therapeutics, Inc. Connector for interfacing intravascular sensors to a physiology monitor
US6668197 Jul 22, 1999 Dec 23, 2003 Imperial College Innovations Limited Treatment using implantable devices
US6673104 Mar 15, 2001 Jan 6, 2004 Scimed Life Systems, Inc. Magnetic stent
US6676694 Jun 6, 2002 Jan 13, 2004 Mitchell Weiss Method for installing a stent graft
US6711429 Sep 24, 1999 Mar 23, 2004 Super Dimension Ltd. System and method for determining the location of a catheter during an intra-body medical procedure
US6712844 Jun 6, 2001 Mar 30, 2004 Advanced Cardiovascular Systems, Inc. MRI compatible stent
US6716237 Sep 18, 2000 Apr 6, 2004 Inflow Dynamics, Inc. Interventional shielded stent delivery system and method
US6765144 Mar 7, 2003 Jul 20, 2004 Nanoset, Llc Magnetic resonance imaging coated assembly
US6767360 Feb 8, 2001 Jul 27, 2004 Inflow Dynamics Inc. Vascular stent with composite structure for magnetic reasonance imaging capabilities
US6782284 Nov 21, 2001 Aug 24, 2004 Koninklijke Philips Electronics, N.V. Method and apparatus for semi-automatic aneurysm measurement and stent planning using volume image data
US6786904 Jan 10, 2002 Sep 7, 2004 Triton Biosystems, Inc. Method and device to treat vulnerable plaque
US6802857 Oct 11, 2000 Oct 12, 2004 Uab Research Foundation MRI stent
US6808535 Apr 28, 2000 Oct 26, 2004 Magforce Applications Gmbh Stent for keeping open tubular structures
US6844492 Sep 13, 2002 Jan 18, 2005 Nanoset, Llc Magnetically shielded conductor
US6884234 Nov 1, 2001 Apr 26, 2005 Cardio Exodus Partners Foldable and remotely imageable balloon
US6908468 Feb 22, 2002 Jun 21, 2005 Mri Devices Daum Gmbh Devices for nuclear spin tomography magnetic resonance imaging (MRI)
US6925322 Jul 25, 2002 Aug 2, 2005 Biophan Technologies, Inc. Optical MRI catheter system
US6957098 Jun 27, 2002 Oct 18, 2005 Advanced Cardiovascular Systems, Inc. Markers for interventional devices in magnetic resonant image (MRI) systems
US20010031919 Feb 13, 2001 Oct 18, 2001 Mediguide Ltd Medical imaging and navigation system
US20020040815 Sep 21, 2001 Apr 11, 2002 Mettler-Toledo Gmbh Balance with a weighing compartment
US20020045816 Mar 26, 2001 Apr 18, 2002 Ergin Atalar Apparatus, systems, and methods for in vivo magnetic resonance imaging
US20020082685 Feb 13, 2001 Jun 27, 2002 Motasim Sirhan Apparatus and methods for controlled substance delivery from implanted prostheses
US20020137014 Mar 5, 2002 Sep 26, 2002 Anderson James H. Simulation method for designing customized medical devices
US20020173724 May 18, 2001 Nov 21, 2002 Dorando Dale Gene Signal conditioning device for interfacing intravascular sensors having varying operational characteristics to a physiology monitor
US20020188345 Jun 6, 2001 Dec 12, 2002 Pacetti Stephen Dirk MRI compatible stent
US20030004562 Jun 29, 2001 Jan 2, 2003 Dicarlo Paul Endoluminal device and monitoring system for detecting endoleaks and/or changes in prosthesis morphology
US20030004563 Jun 29, 2001 Jan 2, 2003 Jackson Gregg A. Polymeric stent suitable for imaging by MRI and fluoroscopy
US20030074049 Nov 5, 2002 Apr 17, 2003 Kensey Nash Corporation Covered stents and systems for deploying covered stents
US20030083579 Nov 1, 2001 May 1, 2003 Cardio Exodus Partners Foldable and remotely imageable balloon
US20030087244 Dec 14, 2001 May 8, 2003 Vitivity, Inc Diagnosis and treatment of vascular disease
US20030088178 Nov 2, 2001 May 8, 2003 Owens Timothy R Method and apparatus for computer modified magnetic resonance imaging
US20030088308 Aug 31, 2002 May 8, 2003 Inflow Dynamics Inc. Primarily niobium stent
US20030092013 Dec 14, 2001 May 15, 2003 Vitivity, Inc. Diagnosis and treatment of vascular disease
US20030096248 Dec 14, 2001 May 22, 2003 Vitivity, Inc. Diagnosis and treatment of vascular disease
US20030099957 Dec 14, 2001 May 29, 2003 Vitivity, Inc. Diagnosis and treatment of vascular disease
US20030100830 Nov 27, 2001 May 29, 2003 Sheng-Ping Zhong Implantable or insertable medical devices visible under magnetic resonance imaging
US20030105069 May 31, 2002 Jun 5, 2003 Robinson Byron C. Metallotetrapyrrolic photosensitizing agents for use in photodynamic therapy
US20030139739 Jan 10, 2002 Jul 24, 2003 Claas Doscher Method and device to treat vulnerable plaque
US20030143544 Jan 9, 2002 Jul 31, 2003 Vitivity, Inc. Diagnosis and treatment of vascular disease
US20030144728 Feb 10, 2003 Jul 31, 2003 Inflow Dynamics Inc. Metal stent with surface layer of noble metal oxide and method of fabrication
US20030153949 Oct 31, 2002 Aug 14, 2003 Lilip Lau Heart failure treatment device and method
US20030163052 Feb 27, 2002 Aug 28, 2003 Mott Eric V. Connector for interfacing intravascular sensors to a physiology monitor
US20030187335 Dec 14, 2001 Oct 2, 2003 Vitivity, Inc. Diagnosis and treatment of vascular disease
US20030199747 Apr 19, 2002 Oct 23, 2003 Michlitsch Kenneth J. Methods and apparatus for the identification and stabilization of vulnerable plaque
US20030212448 May 10, 2002 Nov 13, 2003 Smith John K. Endoluminal device and system and method for detecting a change in pressure differential across an endoluminal device
US20040010304 Jul 10, 2002 Jan 15, 2004 Jan Weber Medical devices and methods of making the same
US20040019376 May 22, 2003 Jan 29, 2004 Inflow Dynamics, Inc. Stent device and method
US20040030379 May 2, 2003 Feb 12, 2004 Hamm Mark A. Energetically-controlled delivery of biologically active material from an implanted medical device
US20040034300 Aug 19, 2002 Feb 19, 2004 Laurent Verard Method and apparatus for virtual endoscopy
US20040038406 Apr 8, 2003 Feb 26, 2004 Genesegues, Inc. Nanoparticle delivery systems and methods of use thereof
US20040039438 Aug 29, 2003 Feb 26, 2004 Inflow Dynamics, Inc., A Delaware Corporation Vascular and endoluminal stents with multi-layer coating including porous radiopaque layer
US20040044397 Aug 28, 2002 Mar 4, 2004 Stinson Jonathan S. Medical devices and methods of making the same
US20040082866 Oct 22, 2003 Apr 29, 2004 Mott Eric V. Connector for interfacing intravascular sensors to a physiology monitor
US20040091603 Jan 7, 2002 May 13, 2004 Jorg Priewe Process for the preparation of a medical implant
US20040093075 Dec 14, 2001 May 13, 2004 Titus Kuehne Stent with valve and method of use thereof
US20040097805 Jul 14, 2003 May 20, 2004 Laurent Verard Navigation system for cardiac therapies
US20040098093 Aug 6, 2003 May 20, 2004 Dicarlo Paul Monitoring system for remote detection of endoleaks and/or changes in morphology of implanted endoluminal devices
US20040111016 Aug 12, 2003 Jun 10, 2004 Texas Heart Institute Method and apparatus for detection of vulnerable atherosclerotic plaque
US20040116997 Sep 22, 2003 Jun 17, 2004 Taylor Charles S. Stent-graft with positioning anchor
US20040117007 Sep 16, 2003 Jun 17, 2004 Sts Biopolymers, Inc. Medicated stent having multi-layer polymer coating
US20040133069 Aug 12, 2003 Jul 8, 2004 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US20040143154 Sep 5, 2003 Jul 22, 2004 Lilip Lau Cardiac harness
US20040143180 Jan 9, 2004 Jul 22, 2004 Sheng-Ping Zhong Medical devices visible under magnetic resonance imaging
US20040158310 Feb 6, 2003 Aug 12, 2004 Jan Weber Medical device with magnetic resonance visibility enhancing structure
US20040210289 Mar 24, 2004 Oct 21, 2004 Xingwu Wang Novel nanomagnetic particles
US20040230271 Feb 17, 2004 Nov 18, 2004 Xingwu Wang Magnetically shielded assembly
US20040243220 Jul 1, 2004 Dec 2, 2004 Abbott Laboratories Vascular Enterprises Limited Methods and apparatus for a curved stent
US20040254419 Jun 14, 2004 Dec 16, 2004 Xingwu Wang Therapeutic assembly
US20040254632 May 7, 2004 Dec 16, 2004 Eckhard Alt Vascular stent with composite structure for magnetic resonance imaging capabilities
US20050004653 Jun 19, 2003 Jan 6, 2005 Scimed Life Systems, Inc. Sandwiched radiopaque marker on covered stent
US20050025797 Jul 7, 2004 Feb 3, 2005 Xingwu Wang Medical device with low magnetic susceptibility
US20050033407 Aug 7, 2003 Feb 10, 2005 Scimed Life Systems, Inc. Stent designs which enable the visibility of the inside of the stent during MRI
US20050049480 Aug 20, 2004 Mar 3, 2005 Biophan Technologies, Inc. Electromagnetic radiation transparent device and method of making thereof
US20050049481 Aug 20, 2004 Mar 3, 2005 Biophan Technologies, Inc. Electromagnetic radiation transparent device and method of making thereof
US20050049482 Aug 20, 2004 Mar 3, 2005 Biophan Technologies, Inc. Electromagnetic radiation transparent device and method of making thereof
US20050049683 Aug 20, 2004 Mar 3, 2005 Biophan Technologies, Inc. Electromagnetic radiation transparent device and method of making thereof
US20050049684 Aug 20, 2004 Mar 3, 2005 Biophan Technologies, Inc. Electromagnetic radiation transparent device and method of making thereof
US20050049685 Aug 20, 2004 Mar 3, 2005 Biophan Technologies, Inc. Electromagnetic radiation transparent device and method of making thereof
US20050049686 Aug 20, 2004 Mar 3, 2005 Biophan Technologies, Inc. Electromagnetic radiation transparent device and method of making thereof
US20050049688 Aug 20, 2004 Mar 3, 2005 Biophan Technologies, Inc. Electromagnetic radiation transparent device and method of making thereof
US20050049689 Aug 20, 2004 Mar 3, 2005 Biophan Technologies, Inc. Electromagnetic radiation transparent device and method of making thereof
US20050065430 Jul 9, 2004 Mar 24, 2005 Andrea Wiethoff Methods of cardiothoracic imaging - (MET-30)
US20050065437 Sep 24, 2003 Mar 24, 2005 Scimed Life Systems, Inc. Medical device with markers for magnetic resonance visibility
US20050079132 Aug 9, 2004 Apr 14, 2005 Xingwu Wang Medical device with low magnetic susceptibility
US20050080459 Oct 9, 2003 Apr 14, 2005 Jacobson Jerry I. Cardioelectromagnetic treatment
US20050085895 Oct 15, 2003 Apr 21, 2005 Scimed Life Systems, Inc. RF-based markers for MRI visualization of medical devices
US20050090886 Oct 22, 2004 Apr 28, 2005 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna geometrical shaped member
US20050107870 Aug 20, 2004 May 19, 2005 Xingwu Wang Medical device with multiple coating layers
US20050113669 Mar 8, 2004 May 26, 2005 Biophan Technologies, Inc. Device and method for preventing magnetic-resonance imaging induced damage
US20050113676 Mar 8, 2004 May 26, 2005 Biophan Technologies, Inc. Device and method for preventing magnetic-resonance imaging induced damage
US20050113873 Mar 8, 2004 May 26, 2005 Biophan Technologies, Inc. Device and method for preventing magnetic-resonance imaging induced damage
US20050113874 Mar 8, 2004 May 26, 2005 Biophan Technologies, Inc. Device and method for preventing magnetic-resonance imaging induced damage
US20050113876 Mar 8, 2004 May 26, 2005 Biophan Technologies, Inc. Device and method for preventing magnetic-resonance imaging induced damage
US20050131522 Dec 10, 2003 Jun 16, 2005 Stinson Jonathan S. Medical devices and methods of making the same
US20050143651 Feb 28, 2005 Jun 30, 2005 Laurent Verard Method and apparatus for virtual endoscopy
US20050149002 Nov 29, 2004 Jul 7, 2005 Xingwu Wang Markers for visualizing interventional medical devices
US20050149157 Nov 22, 2004 Jul 7, 2005 Angiotech International Ag Electrical devices and anti-scarring agents
US20050149169 Oct 27, 2004 Jul 7, 2005 Xingwu Wang Implantable medical device
US20050152946 Dec 7, 2004 Jul 14, 2005 Angiotech International Ag Implantable sensors and implantable pumps and anti-scarring agents
US20050154374 Dec 7, 2004 Jul 14, 2005 Angiotech International Ag Implantable sensors and implantable pumps and anti-scarring agents
US20050155779 Feb 25, 2005 Jul 21, 2005 Xingwu Wang Coated substrate assembly
US20050158356 Nov 22, 2004 Jul 21, 2005 Angiotech International Ag Implantable sensors and implantable pumps and anti-scarring agents
US20050159661 Mar 14, 2005 Jul 21, 2005 Biophan Technologies, Inc. Electromagnetic interference immune tissue invasive system
US20050165470 Jan 22, 2004 Jul 28, 2005 Jan Weber Medical devices
US20050165471 Sep 24, 2004 Jul 28, 2005 Xingwu Wang Implantable medical device
US20050169960 Dec 2, 2004 Aug 4, 2005 Angiotech International Ag Implantable sensors and implantable pumps and anti-scarring agents
US20050169961 Dec 2, 2004 Aug 4, 2005 Angiotech International Ag Implantable sensors and implantable pumps and anti-scarring agents
US20050175664 Dec 2, 2004 Aug 11, 2005 Angiotech International Ag Implantable sensors and implantable pumps and anti-scarring agents
US20050178395 Dec 7, 2004 Aug 18, 2005 Angiotech International Ag Polymer compositions and methods for their use
US20050178396 Dec 7, 2004 Aug 18, 2005 Angiotech International Ag Polymer compositions and methods for their use
US20050178584 Feb 7, 2005 Aug 18, 2005 Xingwu Wang Coated stent and MR imaging thereof
US20050181005 Dec 7, 2004 Aug 18, 2005 Angiotech International Ag Implantable sensors and implantable pumps and anti-scarring agents
US20050181009 Dec 1, 2004 Aug 18, 2005 Angiotech International Ag Implantable sensors and implantable pumps and anti-scarring agents
US20050181010 Dec 1, 2004 Aug 18, 2005 Angiotech International Ag Implantable sensors and implantable pumps and anti-scarring agents
US20050182450 Dec 7, 2004 Aug 18, 2005 Angiotech International Ag Electrical devices and anti-scarring agents
US20050182463 Dec 2, 2004 Aug 18, 2005 Angiotech International Ag Polymer compositions and methods for their use
US20050182467 Dec 7, 2004 Aug 18, 2005 Angiotech International Ag Electrical devices and anti-scarring agents
US20050182468 Dec 7, 2004 Aug 18, 2005 Angiotech International Ag Electrical devices and anti-scarring agents
US20050182469 Dec 7, 2004 Aug 18, 2005 Angiotech International Ag Electrical devices and anti-scarring agents
US20050183731 Dec 7, 2004 Aug 25, 2005 Angiotech International Ag Polymer compositions and methods for their use
US20050186239 Dec 7, 2004 Aug 25, 2005 Angiotech International Ag Implantable sensors and implantable pumps and anti-scarring agents
US20050186244 Dec 2, 2004 Aug 25, 2005 Angiotech International Ag Polymer compositions and methods for their use
US20050186245 Dec 7, 2004 Aug 25, 2005 Angiotech International Ag Implantable sensors and implantable pumps and anti-scarring agents
US20050187140 Nov 29, 2004 Aug 25, 2005 Angiotech International Ag Polymer compositions and methods for their use
US20050187582 Feb 20, 2004 Aug 25, 2005 Biophan Technologies, Inc. Fibrillation/tachycardia monitoring and preventive system and methodology
US20050187600 Nov 26, 2004 Aug 25, 2005 Angiotech International Ag Electrical devices and anti-scarring agents
US20050192647 Dec 7, 2004 Sep 1, 2005 Angiotech International Ag Electrical devices and anti-scarring agents
US20050196421 Dec 1, 2004 Sep 8, 2005 Angiotech International Ag Polymer compositions and methods for their use
US20050197527 Mar 4, 2004 Sep 8, 2005 Bolling Steven F. Adjustable heart constraining apparatus and method therefore
US20050209664 Nov 26, 2004 Sep 22, 2005 Angiotech International Ag Electrical devices and anti-scarring agents
US20050209665 Nov 26, 2004 Sep 22, 2005 Angiotech International Ag Electrical devices and anti-scarring agents
US20050209666 Dec 7, 2004 Sep 22, 2005 Angiotech International Ag Electrical devices and anti-scarring agents
US20050215764 Feb 18, 2005 Sep 29, 2005 Tuszynski Jack A Biological polymer with differently charged portions
US20050216075 Jan 28, 2005 Sep 29, 2005 Xingwu Wang Materials and devices of enhanced electromagnetic transparency
WO2003037217A1 Oct 31, 2002 May 8, 2003 Paracor Medical, Inc. Heart failure treatment device
WO2004021927A2 Sep 5, 2003 Mar 18, 2004 Paracor Medical, Inc. Cardiac harness
1 Applicant's Amendment and Response dated Dec. 19, 2007 to Examiner's Office Action dated Sep. 24, 2007 (34 pgs.).
2 Applicant's Amendment and Response dated Sep. 4, 2008 to Examiner's Office Action dated Jun. 18, 2008 (14 pgs.).
3 Applicant's Restriction Response dated Aug. 13, 2007 to Examiner's Restriction Requirement dated Jul. 13, 2007 (7 pgs.).
4 International Search Report. Dec. 28, 2006. 4 pgs.
5 United States Patent and Trademark Office Office Action for related U.S. Appl. No. 11/215,666 dated Jun. 18, 2008 (21 pgs.).
6 United States Patent and Trademark Office Office Action for related U.S. Appl. No. 11/215,666 dated Sep. 24, 2007 (23 pgs.).
7 United States Patent and Trademark Office Restriction Requirement for related U.S. Appl. No. 11/215,666 dated Jul. 13, 2007 (6 pgs.).
Cooperative Classification A61N1/362, A61F2/2481