Patent Description:
The present invention generally relates to an occlusion device for occluding a cardiovascular defect or a gap between a medical device and adjacent body tissue and a system comprising the occlusion device and a delivery system cooperating therewith.

There are several types of unnecessary or even pathologic passageways within the body. If located in blood vessels or in the heart, such passageways can cause a highly undesirable alteration of blood flow or the bypass of blood flow around an organ.

<CIT> describes a method and a device for blocking a body passageway by inserting an expandable frame into the passageway and expanding the frame with an expandable balloon to partially embed the frame in the walls of the passageway. The frame can be provided with a separate sealing membrane, or the balloon can function as the sealing membrane. The balloon can be removed along with the inflation tube after the expansion step if it is not serving as the sealing membrane, or the balloon can be detached from the inflation tube and left in place, either as a sealing membrane or simply to lock the frame in place. The frame can be maintained in its expanded state by being plastically deformed during the expansion step. The expandable frame has substantially cylindrical shape and is described as being suitable, e.g., for closing a patent ductus arteriosus, in which an unwanted passageway or duct connects the aorta to the main pulmonary artery, close to the heart.

<CIT> describes a device for effecting closure of a perforation in the septum of the heart. The device comprises a double-balloon septal defect occlusion catheter which is to be inserted such that the two initially deflated balloons are positioned on opposing sides of the septum. Upon inflating, the balloons snugly engage the respective septum wall sections and thereby prevent leakage through the perforation.

Paravalvular leak is a common complication that occurs in up to <NUM>% of patients undergoing implantation of either surgical or transcatheter prostheses. The option to treat these defects percutaneously may offers safer solution for high-risk patients, without exposing them to risk related to open heart reoperation. However, the currently used devices are suboptimal since they have not been specifically developed with this intended use. Today, paravalvular leak closure is generally accomplished with devices originally designed for occlusion of congenital heart defects. They are usually implanted in a low-flow environment such as patent foramen ovale or atrial septum defect, and in simple geometries. In contrast, paravalvular leaks develop in high pressure and flow environment, and they are characterized by complex geometry. The defect is often crescent or oval shaped, which may include a tubular section with several deformities, and the structure is marginally compliant at best.

The left atrial appendage (LAA) is a cavity that presents in the left atrium of the heart. In patients with atrial fibrillation the passage and steadiness of blood within this cavity can cause thrombus formation, which increase the risk of stroke. Percutaneous LAA occlusion is a therapy for the prevention of stroke in patients with atrial fibrillation. LAA occlusion is used as an alternative to, or in combination with, oral anticoagulant therapy. LAA occlusion has favorable clinical outcomes, but commercially-available devices are typically self-expandable, and not designed to adapt to the anatomy, thus sometimes resulting in complications or suboptimal outcomes. In these environments, some of the currently available occlusion devices are limited by the poor adaptability of the device to the defect (lack of conformability) and by a lack of intra-device sealing (due to the high flow environment).

Nevertheless, there are some concepts and implementations of occlusion devices that were specifically designed for paravalvular leak occlusion or LAA occlusion.

<CIT> describes various devices for occluding a gap between a medical device and adjacent body tissue. The devices generally comprise a conformable body with a hollow interior and provided with a fluid port intended to supply a pressurizing fluid to inflate the conformable body. Various shapes and constitutions of the conformable body, delivery means and fixing means are described.

<CIT> generally describes a multitude of concepts for locating and for repairing paravalvular leaks. The concepts include sealing stents and also multicomponent and radiation-cured adhesive compounds.

<CIT> describes an occluder device for closing a passage in a circulatory system. The device comprises an expandable fixation unit for fixing the occluder on the passage, which is achieved by switching between a compact form and an expanded form.

<CIT> discloses a medical retainer capable of independently controlling supplying air and water to a hollow organ like a stomach and a lumen of a small intestine.

<CIT> discloses a method of effecting the occlusion of a blood vessel by forming an access opening in the body of the patient communicating with the desired blood vessel, introducing an occlusion member in the vessel, moving the member to the desired point of occlusion, and thereat expanding the member to a size greater than the diameter of the vessel whereby the member is substantially immovably retained therein.

<CIT> discloses that a medical device for reducing the volume of a left atrial appendage (LAA) may include an elongate shaft having a distal portion, and a volume-reducing means expandable from a collapsed to an expanded state, the volume-reducing means being releasably attached to the distal portion.

In spite of the above, there is still a need for an improved occlusion device which avoids the shortcomings of presently known devices.

In some applications of the present invention, an occlusion device is provided for occluding a cardiovascular defect or a gap between a medical device and adjacent body tissue. The occlusion device is for use with a guidewire and a delivery system. The occlusion device comprises:.

According to another aspect, there is provided an occlusion system comprising an occlusion device as described above and a delivery system (comprising a catheter device) cooperating therewith. The catheter device comprises an implant catheter tube connected to an operating handle. The implant catheter tube comprises a longitudinal passageway for a guidewire, a distal connection element for releasably connecting the catheter device to a correspondingly configured proximal connection element of the occlusion device, and a fluid transfer system releasably connectable to a corresponding inflation port of the occlusion device. The distal connection element and the proximal connection element are generally configured as cooperating members disposed, respectively, at the distal end of the catheter device and at the proximal end of the occlusion device. Examples for such cooperating members comprise cooperating threads, bayonets, or snap connections.

Clinical indications include but are not limited to paravalvular leak (PVL), patent foramen ovale (PFO), atrial septum defect (ASD), ventricular septum defect (VSD), intravalvular leak (IVL), intraleaflet leak, leaflet perforation, type I endovascular leaks after vascular graft implant, left or right heart apex closure after transapical therapeutic access, and left atrial appendage occlusion.

The occlusion device is designed to be delivered into the region to be treated in its longitudinally extended form, either entirely or partially compressed. After delivery, the occlusion device is adapted to the landing zone anatomy by inflating the balloon and subsequently shortening of the longitudinal dimension of the frame formed between the proximal base element and the distal tip element. Under the influence of internal pressure, the balloon will assume a certain volume which, for a given longitudinal frame dimension, results in a certain lateral or radial dimension, which provides a good seal between the balloon and the adjacent anatomy or implanted medical device. Changing the longitudinal frame dimension by selecting a different distance between the distal tip element and the proximal base element will lead to a corresponding change in the radial or lateral extension of the balloon. In other words, shortening the distance between the distal tip element and the proximal base element leads to a corresponding increase in radial or lateral extension under otherwise constant conditions, which improves the seal with the adjacent tissue and/or medical device and seals unwanted blood passage. The lateral extension of the balloon is not necessarily symmetric, either because the balloon is not necessarily symmetric and/or because the anatomy against which the balloon is laterally expanded may cause asymmetric balloon expansion. The radial or lateral expansion together include within their scope one or more directions generally perpendicular to the longitudinal axis of the balloon. (Optionally, the balloon is partially inflated (e.g., to atmospheric pressure) and the longitudinal dimension of the frame is shortened; the balloon may subsequently be further inflated before release, such as if necessary to make the good seal between the balloon and the adjacent anatomy or implanted medical device.

In the context of the present disclosure, the terms "distal" and "proximal" are used accordingly to their standard meaning in the field of percutaneous cardiovascular devices. The term "proximal" refers to those components of the device assembly which, when following a delivery catheter during percutaneous delivery, are closer to the end of the catheter that is configured for manipulation by the user (e.g., catheter handle manipulated by a physician). The term "distal" is used to refer to those components of the device assembly that are more distant from the end of the catheter that is configured for manipulation by the user and/or that are inserted further into the body of a patient. Accordingly, in an occlusion device for use in a gap between a medical device and the adjacent body tissue, like a paravalvular mitral leak, the proximal end may face towards the left atrium and the distal end may face towards the left ventricle, when the occlusion device is deployed in the defect using a transseptal approach.

The term "compliant" used in relation with balloons or with structural components shall be understood as implying a deformability that substantially follows an applied force. Accordingly, a "compliant balloon" shall be understood as a balloon which progressively expands under the effect of increasing radial pressure as long as a certain burst pressure is not exceeded.

The term "strut" shall be understood as an elongate structural element which can be formed e.g. as a thin wire, rod, thick-walled tube, all of which do not necessarily have a circular cross section.

The compliant balloon of the occlusion device is not necessarily pre-shaped since the balloon, because it is compliant, takes the shape of the defect once inflated within the defect. However, for some applications, the wall of the balloon has a different thickness in a specific area (e.g., centrally, such that the balloon assumes a figure-eight shape upon inflation, or longitudinally on one side, to create a backbone that causes the balloon to inflate less on that side). In addition, pre-shaped balloons can be used to establish a predetermined, non-uniform local resilience against an applied radial pressure.

For some applications, the balloon comprises silicone, polyurethane, polytetrafluoroethylene (PTFE), polymethylmethacrylate, polyether ether ketone (PEEK), polyvinyl chloride, polyethylene terephthalate, nylon, polyamide, polyamide, polyether block amide (PEBA), or another biocompatible material. For some applications, the balloon comprises a compliant, biodegradable material selected from polycaprolactone (PCL), polyglycolic acid (PGA), polylactic acid (PLA), and polydioxanone (PDO or PDS). Optionally, the balloon is treated externally with a hydrophilic coating, hydrophobic coating, an anti-inflammatory coating, anticoagulation coating, or other coating to promote endothelial growth, such as chemically or by modifying the porosity of the external surface of the balloon.

For some applications, the proximal base element and the distal tip element are connected by one or more struts. Depending on the specific application, various configurations of the struts may be contemplated. According to one application, the struts comprise a single connecting strut disposed within the balloon lumen or outside the balloon. For other applications, the struts comprise a plurality of struts, e.g., disposed in a cage-like manner outside the balloon. Applying internal pressure to the balloon will lead to inflation thereof against a resilient force of the compliant balloon material and also against the structural limitation provided by the plurality of external connecting struts. In particular, such a configuration may offer the advantage of an improved stability of the compliant balloon against unwanted local deformation. This will generally result in an improved adaptation of the occlusion device to the geometry of the defect to be occluded.

The locking mechanism for maintaining a predetermined distance between the distal tip element and the proximal base element may also be configured in various manners. For example, the locking mechanism may comprise a rotatable elongate actuating element (e.g., a wire) with a threaded portion formed to cooperate with a corresponding section formed in the proximal base element. For some applications, the locking mechanism is configured as a ratchet mechanism such that the distance between the distal tip element and the proximal base element is selectable from a range of distances. This allows for precise and reliable definition of the radial extension of the occlusion device and accordingly to improved reliability of the occlusion device.

The elongate actuating element is disposed longitudinally slidable in the balloon lumen, connected to the distal tip element and longitudinally slidable with respect to the proximal base element so as to set a distance between the distal tip element and the proximal base element. For this purpose, the elongate actuating element is typically formed as an elongate, flexible member with a smooth surface. For some applications, the elongate actuating element is configured as actuating wire. The use of actuating wires is well established in the field of cardiovascular interventions. In the present context, the use of a wire together with appropriate proximal counterpieces allows for simple, precise and reproducible selection of the distance between the distal tip element and the proximal base element.

Means for filling and unfilling balloons and other inflatable devices are also well known in the field of cardiovascular interventions. For some applications, the balloon has an inflation port configured as a self-closing valve when it is not connected to a corresponding fluid transfer system of the delivery system. In particular, this allows filling the balloon through a longitudinal fluid line which can subsequently be disconnected and retracted and which only needs to be reinserted and reconnected if an additional filling or an unfilling of the balloon is needed.

The aforementioned elements as well as those claimed and described in the following and to be used according to the invention, shall generally be understood with their meaning as established in the field of medicine.

The above mentioned and other features and objects of this invention and the manner of achieving them will become more apparent and this invention itself will be better understood by reference to the following description of various embodiments of this invention taken in conjunction with the accompanying drawings, in which:
The present invention will be more fully understood from the following detailed description of embodiments thereof, taken together with the drawings, in which:.

It will be understood that the figures are not necessarily drawn to scale. In some instances, relative dimensions may be substantially distorted for ease of visualization.

<FIG> shows a cross-sectional view of an expanded occlusion device <NUM>. <FIG> show side elevational views of the occlusion device <NUM> illustrated in <FIG>. Occlusion device is for use with a guidewire <NUM> and a delivery system <NUM> (shown in <FIG>). As shown, the occlusion device <NUM> comprises a compliant balloon <NUM> having a central balloon lumen <NUM> forming a longitudinal passage <NUM> through an interior of the balloon <NUM> from a proximal side 28A to a distal side 28B of the balloon <NUM>. The balloon <NUM> defines a fluid-tight balloon chamber <NUM>. The balloon <NUM> is typically compliant, as defined above. Optionally, the balloon lumen <NUM> is foldable, such that the balloon lumen <NUM> closes on itself after the guidewire <NUM> (shown in <FIG>) is removed, so not to leave an open passage within the occlusion device <NUM>. For example, the foldability of the balloon lumen <NUM> may be provided by providing proximal and distal valves on the entrances of the balloon lumen <NUM>, or by configuring the balloon lumen <NUM> to collapse and fold longitudinally.

The occlusion device <NUM> further comprises a frame <NUM> comprising a proximal base element <NUM> and a distal tip element <NUM>, disposed at the proximal and distal sides 28A and 28B of the balloon <NUM>, respectively, and connected by an elongate actuating element <NUM> passing and longitudinally slidable within the central lumen <NUM> of the balloon <NUM>. The elongate actuating element <NUM> is longitudinally moveable with respect to the proximal base element <NUM> so as to set a distance between the distal tip element <NUM> and the proximal base element <NUM>. Typically, the elongate actuating element <NUM> is selected from the group consisting of: a tube, a wire, a shaft, a cable, a strand, and a fiber. Reduction of the distance may cause the distal tip element <NUM> to move toward the proximal base element <NUM>, the proximal base element <NUM> to move toward the distal tip element <NUM>, or both movements.

For some applications, the proximal base element <NUM> and the distal tip element <NUM> comprise a proximal disk <NUM> and a distal disk <NUM>, respectively. The frame <NUM> provides structural support to the balloon <NUM>. The frame <NUM> may be formed from a cut structure so that each component of the frame <NUM> is integrally connected with each other. The elongate actuating element <NUM> may have a linear or nonlinear section and may have plastic or metallic deformable characteristics.

The occlusion device <NUM> further comprises a locking mechanism <NUM> for maintaining, between the distal tip element <NUM> and the proximal base element <NUM>, the distance set using the elongate actuating element <NUM>. For example, the locking mechanism <NUM> may comprise a crimping element, a threaded element, a locking element, an inflatable balloon, a locking wire, or a ratchet element. For some applications, the locking mechanism <NUM> is disposed at the proximal side 28A of the balloon <NUM>, for example, connected to or integrated into the proximal base element <NUM>.

The occlusion device <NUM> is shaped so as to form a closed three-dimensional shape. The occlusion device <NUM> comprises a proximal connection element <NUM> that is configured to attach the occlusion device <NUM> to and release the occlusion device <NUM> from delivery system <NUM>, e.g., from an implant catheter <NUM> of delivery system <NUM>. It is noted that the longitudinal passage <NUM> is still defined through the interior of the balloon <NUM> after release of the occlusion device <NUM> from the implant catheter <NUM>. Typically, when the occlusion device <NUM> is connected to the implant catheter <NUM>, no portion of the implant catheter <NUM> is disposed within the interior of the balloon <NUM>.

Typically, the proximal base element <NUM> and the distal tip element <NUM> (e.g., the proximal and distal disks <NUM> and <NUM>) are shaped so as to define respective guidewire openings 105a and 105b substantially coaxial to the balloon lumen <NUM> for slidingly receiving therein guidewire <NUM> (shown in <FIG>) for delivering the occlusion device <NUM>.

For some applications, the proximal base element <NUM> and the distal tip element <NUM> (e.g., the proximal and distal disks <NUM> and <NUM>) are deformable, such as to allow the elements to automatically adjust their shapes upon inflation of the balloon <NUM>. Alternatively, the proximal base element <NUM> and the distal tip element <NUM> (e.g., the proximal and distal disks <NUM> and <NUM>) are not deformable.

For some applications, the proximal base element <NUM> and the distal tip element <NUM> (e.g., the proximal and distal disks <NUM> and <NUM>) comprise a plastic or a metal, e.g., Nitinol.

Although the proximal and distal disks <NUM> and <NUM> are shown as circular in the figures, the disks may have other shapes, such as the shape of a flower, a cross, a star, an ellipse, or any other shape as necessary or appropriate for proper cardiovascular defects occlusion and device stabilization. The proximal and distal disks <NUM> and <NUM> are typically radially symmetric, but may also be asymmetric.

The occlusion device <NUM> further comprises an inflation port <NUM> entering into the balloon <NUM> along a central axis of the balloon <NUM> or elsewhere, such as in close vicinity of the central axis. The inflation port <NUM> is releasably connected to an inflation tube channel of the implant catheter <NUM> and allows inflation and deflation of the balloon <NUM> while connected before release of the occlusion device <NUM> from the implant catheter <NUM>. Within the central lumen <NUM> of the balloon <NUM>, the balloon <NUM> may define a guidewire lumen <NUM> allowing guidewire <NUM> (shown in <FIG>) to freely move axially through the occlusion device <NUM>. Typically, in configurations in which the proximal opening of the guidewire lumen <NUM> is centered around the central axis of the balloon <NUM>, the inflation port <NUM> is off-center, and vice versa.

According to an application of the present invention, the compliant balloon <NUM> may be inflated by filling the balloon chamber <NUM> with any fluid, including but not limited to saline solution (optionally comprising a contrast medium), blood (e.g., autologous blood), foam, and a glue (e.g., a gel, a liquid polymer that can change its proprieties to become rigid, or a hydrogel that remains a gel or self-cures at body temperature). For applications in which the fluid includes autologous blood, the autologous blood may be drawn from the patient during the deployment of the occlusion device <NUM>, e.g., at a location proximal to the balloon <NUM> within the patient's body, or drawn from the patient outside the patient's body and filled into the balloon chamber <NUM> via the deployment system. For applications in which the fluid includes blood, an anti-coagulation agent may be mixed with the blood in order to delay coagulation for a while in case the balloon <NUM> must be retrieved; eventually the blood coagulates.

The above-mentioned fluid provides the long-term shape setting, sealing and occluding properties of the expanded occlusion device <NUM>. The balloon <NUM> provides the acute, i.e., immediate shape setting, sealing, and occluding properties of the expanded occlusion device <NUM>. Therefore, for applications in which occlusion device <NUM> is radiopaque and is implanted in a beating heart under echocardiographic, fluoroscopic, and/or x-ray guidance, upon inflation of the balloon <NUM>, the surgeon can immediately observe whether the defect has been occluded (by observing cessation of blood flow through the defect). The immediate closure of the defect upon inflation of the balloon <NUM> contrasts with known closure devices comprising a braided wire mesh, which generally do not provide immediate closure of the defect, but instead only provide good closure upon sufficient blood clotting in the mesh after several days or weeks. Thus the effectiveness of these known closure devices can generally only be evaluated at least several days after implantation.

The implant catheter <NUM> and the inflation port <NUM> may contain specific channels, valves and membranes designed to be compatible with the fluid used, including filter membranes that can be permeable to blood in the case blood is used as filling fluid of the balloon chamber <NUM>.

Moreover, the frame <NUM> allows longitudinal adjustment of the balloon <NUM> to enhance the stability of the occlusion device <NUM> and to enhance occlusion of the defect.

In some applications, the frame <NUM> may be designed to have a limited conformability (for example, because of the thickness of the frame <NUM> or a material property of the frame <NUM>), such as in order to create a tapered shape to provide asymmetrical confinement to the balloon <NUM>, for example, tapered at the distal end, such that the balloon <NUM> has a pear shape when constrained by anatomy or otherwise constrained. The frame <NUM> may have a generally conical, or frustoconical shape, cylindrical shape, or any other shape as necessary or appropriate. In some application, the balloon <NUM> is configured to have limited conformability in some sections of the balloon, such as in order to create a figure-eight shape or a tapered shape, or an asymmetrical shape when expanded under inflation.

In some applications, frame <NUM> further comprises a single strut <NUM> passing inside and tapering the balloon <NUM> component. The strut <NUM> may or may not be fixed to the inner surface of the balloon <NUM> or embedded in the balloon <NUM>, as described hereinbelow with reference to <FIG>. Optionally, the strut <NUM> passes through the central lumen <NUM> of the balloon <NUM> (configuration not shown).

<FIG> illustrate further optional features that may be provided in conjunction with the occlusion device <NUM> as presented in the application of <FIG>. In order to avoid repetitions, only those features differing from the occlusion device described above will be addressed. Like reference numbers denominate the same or corresponding features.

<FIG> shows a cross-sectional view of an expanded occlusion device <NUM>. <FIG> show side elevational views of the occlusion device <NUM> illustrated in <FIG>. Occlusion device <NUM> comprises a frame <NUM>, which may comprise the proximal base element <NUM> and the distal tip element <NUM> (e.g., the proximal and distal disks <NUM> and <NUM>), connected by a plurality of struts <NUM>, which may have any suitable form, passing inside (not shown) or outside (as shown) and tapering the balloon <NUM> component. Such an application may allow a cage-like structural confinement of the balloon <NUM> within its assembly, to avoid unnecessary interference of the occlusion device <NUM> with the body tissue or with implanted prostheses and to provide anchoring support of the occlusion device <NUM> within the defect, e.g., the cardiovascular defect. In this application, the frame <NUM> may comprise <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM> or any other suitable even or odd number of struts <NUM>. The struts <NUM> may be disposed inside or outside the balloon <NUM>. For some applications, the struts <NUM> are not fixed to any surfaces of the balloon <NUM>. For other applications, the struts <NUM> are (a) fixed to a surface (inner or outer) of the balloon <NUM>, (b) embedded in the wall of the balloon <NUM> during manufacture (such as by being cast within the wall). Alternatively, the balloon <NUM> may be molded over the struts <NUM>, which remain internally fixed to the balloon <NUM>.

In some applications, the struts <NUM> forming the frame <NUM> may differ in wall thickness and/or width along their entire length or a section thereof. As such, a strut <NUM> may have a first section that is wider than a second section. In other applications, a middle or a distal end section of a strut <NUM> may be provided with a larger or smaller wall thickness and/or strut width. Varying the wall thickness and/or the strut <NUM> width may determine the frame <NUM> radial stability.

<FIG> shows a cross-sectional view of an expanded occlusion device <NUM>. <FIG> show side elevational views of the occlusion device <NUM> illustrated in <FIG>. Occlusion device <NUM> comprises a frame <NUM> may comprise the proximal base element <NUM> and the distal tip element <NUM> (e.g., the proximal and distal disks <NUM> and <NUM>), connected by one strut <NUM> passing outside and tapering the balloon <NUM> component. The strut <NUM> may or may not be fixed to the inner surface (not shown) or the outer surface (as shown) of the balloon <NUM> or embedded in the balloon <NUM>, as described hereinabove with reference to <FIG>.

Reference is now made to <FIG>, which shows a cross-sectional view of an expanded occlusion device <NUM>. Reference is also made to <FIG>, which show side elevational views of the occlusion device <NUM> illustrated in <FIG>.

Reference is also made to <FIG>, which is a cross-sectional view of the occlusion device <NUM> illustrated in <FIG> after actuation of the ratchet mechanism <NUM> described below and longitudinal shortening. Reference is also made to <FIG>, which show side elevational views of the occlusion device <NUM> illustrated in <FIG>.

As shown in <FIG>, in this configuration the elongate actuating element <NUM> comprises an elongate actuating element <NUM> that is fixedly connected to the distal tip element <NUM>. The elongate actuating element <NUM> comprises a plurality of teeth <NUM>, and the locking mechanism <NUM> comprises one or more pawls. The elongate actuating element <NUM> and the pawls of the locking mechanism together provide a ratchet mechanism <NUM>, such that the distance between the distal tip element <NUM> and the proximal base element <NUM> is selectable from a range of distances by distally pulling the elongate actuating element <NUM> through the locking mechanism <NUM>. This ratchet mechanism <NUM> allows longitudinal adjustment of the occlusion device <NUM> in one direction, while inhibiting movement in the other direction, so that the proximal base element <NUM> and the distal tip element <NUM> can only come closer to each other, before device <NUM> is released from the implant catheter <NUM>, as shown in <FIG>. Optionally, any excess proximal portion of the elongate actuating element <NUM> that extends through the proximal base element <NUM> to outside the occlusion device <NUM> is cut and removed from the body; to this end, the elongate actuating element <NUM> may be perforated or have weaker (e.g., thinner) axial portions that are configured to break upon application of a breaking force.

Also as shown in <FIG>and <FIG>, occlusion device <NUM> optionally is configured to assume a figure-eight shape upon inflation. For example, the figure-eight shape may be achieved by the thickness of an axial central portion of the struts <NUM>, or by a limiting band that connect the struts <NUM> at that axial position of the narrower central portion of the figure eight, or by the thickness of the balloon <NUM> that results in less inflation in the narrower central portion of the figure eight.

Reference is now made to <FIG>, which shows a cross-sectional view of an expanded occlusion device <NUM>. Reference is also made to <FIG>, which shows a side elevational view of the occlusion device <NUM> illustrated in <FIG>. Except as described below, occlusion device <NUM> is identical to occlusion device <NUM>, described hereinabove with reference to <FIG> and <FIG>.

As shown in <FIG>, in this configuration the elongate actuating element <NUM> comprises an elongate actuating element <NUM> that is fixedly connected to the distal tip element <NUM>. The elongate actuating element <NUM> is shaped so as to define a thread <NUM>, and the locking mechanism <NUM> comprises a threaded opening defined by the proximal base element <NUM>. The thread <NUM> of the elongate actuating element <NUM> is disposed within the threaded opening. The occlusion device <NUM> is configured such that rotation of the elongate actuating element <NUM> with respect to the proximal base element <NUM> causes the elongate actuating element <NUM> to longitudinally move with respect to the proximal base element <NUM>, thereby setting the distance between the distal tip element <NUM> and the proximal base element <NUM> and maintaining the set distance. This arrangement allows both shortening of the distance and subsequent lengthening if necessary. For some applications, the locking mechanism <NUM> is disposed at the proximal side 28A of the balloon <NUM>, for example, connected to or integrated into the proximal base element <NUM>. Optionally, any excess proximal portion of the elongate actuating element <NUM> that extends through the proximal base element <NUM> to outside the occlusion device <NUM> is cut and removed from the body.

Reference is still made to <FIG>. Alternatively, the elongate actuating element <NUM> is not shaped so as to define the thread <NUM>, and the locking mechanism <NUM> comprises a non-threaded opening defined by the proximal base element <NUM>. Proximally pulling the elongate actuating element <NUM> sets the distance between the distal tip element <NUM> and the proximal base element <NUM>. Once the desired distance has been set, the locking mechanism <NUM> is locked to fix the elongate actuating element <NUM> with respect to the proximal base element <NUM>. For some applications, the locking mechanism <NUM> is disposed at the proximal side 28A of the balloon <NUM>, for example, connected to or integrated into the proximal base element <NUM>.

Reference is now made to <FIG>, which shows a cross-sectional view of an expanded occlusion device <NUM>. Reference is also made to <FIG>, which shows a side elevational view of the occlusion device <NUM> illustrated in <FIG>. Except as described below, occlusion device <NUM> is identical to occlusion device <NUM>, described hereinabove with reference to <FIG>.

As shown in <FIG>, in this configuration the elongate actuating element <NUM> comprises an elongate actuating element <NUM> that is fixedly connected to the distal tip element <NUM>. The locking mechanism <NUM> comprises a spool assembly <NUM>, comprising a spool and, typically, a housing enclosing the spool. A proximal portion of the elongate actuating element <NUM> is wound around the spool. The occlusion device <NUM> is configured such that rotation of the spool causes the elongate actuating element <NUM> to longitudinally move with respect to the proximal base element <NUM>, thereby setting the distance between the distal tip element <NUM> and the proximal base element <NUM> and maintaining the set distance. This arrangement allows both shortening of the distance and subsequent lengthening if necessary. For some applications, the locking mechanism <NUM> is disposed at the proximal side 28A of the balloon <NUM>, for example, connected to or integrated into the proximal base element <NUM>.

Reference is now made to <FIG>, which shows a cross-sectional view of an expanded occlusion device <NUM>. Reference is also made to <FIG>, which shows a side elevational view of the occlusion device <NUM> illustrated in <FIG>. Except as described below, occlusion device <NUM> is similar to occlusion device <NUM>, described hereinabove with reference to <FIG>.

As shown in <FIG>, in this configuration the elongate actuating element <NUM> comprises an elongate actuating element <NUM> that is axially fixedly connected to a proximal base element <NUM>. The elongate actuating element <NUM> is shaped so as to define a thread <NUM>, and the locking mechanism <NUM>, which is disposed at the distal side 28B of the balloon <NUM>, comprises a threaded opening defined by a distal tip element <NUM>. The thread <NUM> of the elongate actuating element <NUM> is disposed within the threaded opening. The occlusion device <NUM> is configured such that rotation of the elongate actuating element <NUM> with respect to the distal tip element <NUM> causes the elongate actuating element <NUM> to longitudinally move with respect to the distal tip element <NUM>, thereby setting the distance between the distal tip element <NUM> and the proximal base element <NUM> and maintaining the set distance. This arrangement allows both shortening of the distance and subsequent lengthening if necessary. This configuration is appropriate for implantation locations in which the excess distal portion of the elongate actuating element <NUM> that protrudes from the distal side 28B of the occlusion device <NUM> upon shortening of the device does not interfere with the anatomy, such as in the LAA, as described hereinbelow with reference to <FIG>.

Optionally, the proximal base element and a proximal portion of the elongate actuating element <NUM> together comprise a rotational ratchet mechanism <NUM>, which is configured to allow rotation of the elongate actuating element <NUM> in only one rotational direction.

Reference is now made to <FIG>, which shows a cross-sectional view of an expanded occlusion device <NUM>. Occlusion device <NUM> comprises a locking elongate element <NUM> that (a) passes through the locking mechanism <NUM> within the central lumen <NUM> and (b) is fixed to a distal tip element <NUM>. The locking elongate element <NUM> is longitudinally slidable with respect to the proximal base element <NUM>. Typically, the locking elongate element <NUM> is selected from the group consisting of: a tube, a wire, a shaft, a cable, a strand, and a fiber.

In this configuration, elongate actuating element <NUM> comprises an elongate actuating element <NUM> that is disposed within the central lumen <NUM>, is releasably connected to the distal tip element <NUM>, and is longitudinally slidable with respect to the proximal base element <NUM>. Typically, the elongate actuating element <NUM> is selected from the group consisting of a tube, a wire, a shaft, a cable, a strand, and a fiber. After longitudinal adjustment of the length of the occlusion device <NUM> by adjusting the distance between the proximal base element <NUM> and the distal tip element <NUM> by pulling and/or pushing the elongate actuating element <NUM>, the locking mechanism <NUM> is activated, thereby securing the locking elongate element <NUM> within the locking mechanism <NUM> in the proximal base element <NUM> through which the locking wire <NUM> passes, in order to maintain fixed the distance between the proximal base element <NUM> and the distal tip element <NUM> set using the elongate actuating element <NUM>. For some applications, the locking mechanism <NUM> is disposed at the proximal side 28A of the balloon <NUM>, for example, connected to or integrated into the proximal base element <NUM>.

The elongate actuating element <NUM> may be pulled and/or pushed directly by the user, in which case the axial movement of the elongate actuating element <NUM> pulls or pushes the distal tip element <NUM> in the direction of the proximal base element <NUM>. Pulling or pushing the elongate actuating element <NUM> also causes corresponding motion of the locking elongate element <NUM> through the proximal base element <NUM>, typically as a result of sufficient axial stiffness of the locking elongate element <NUM>.

After the desired distance has been set and the locking mechanism <NUM> has locked the locking elongate element <NUM>, the elongate actuating element <NUM> is released from the distal tip element <NUM>, and removed from the occlusion device <NUM> and the patient's body. For example, a distal portion <NUM> of the elongate actuating element <NUM> may be shaped so as to define a thread <NUM>, and the distal tip element <NUM> may be shaped so as to define a threaded opening to which the thread <NUM> of the distal portion <NUM> of the elongate actuating element <NUM> is releasably threadingly connected, such that the elongate actuating element <NUM> is releasably connected to the distal tip element <NUM>. The elongate actuating element <NUM> is released from the distal tip element <NUM> by rotating the elongate actuating element <NUM>, thereby unscrewing it from the distal tip element <NUM>. Alternatively, for example, the elongate actuating element <NUM> may be releasably connected to the distal tip element <NUM> using first and second positive connection elements, such as described hereinbelow with reference to <FIG>.

It is noted that in this configuration, and in other configurations in which the elongate actuating element <NUM> is releasably connected to the distal tip element <NUM>, the elongate actuating element <NUM> is not an element of the occlusion device <NUM>, and indeed is disconnected from the occlusion device <NUM> during the implantation procedure and removed from the body.

Optionally, any excess proximal portion of the locking elongate element <NUM> that extends through the proximal base element <NUM> to outside the occlusion device <NUM> is cut and removed from the body.

Reference is now made to <FIG>, which shows a cross-sectional view of an expanded occlusion device <NUM>. Other than as described below, occlusion device <NUM> is identical to occlusion device <NUM>, described hereinabove with reference to <FIG>.

In this configuration, elongate actuating element <NUM> comprises an elongate actuating element <NUM>, which, other than as described below, is similar to elongate actuating element <NUM>, described hereinabove with reference to <FIG>. The elongate actuating element <NUM> is shaped so as to define a thread <NUM>. The proximal base element <NUM> is shaped so as to define a threaded opening, and the thread <NUM> of the elongate actuating element <NUM> is disposed within the threaded opening. Typically, the elongate actuating element <NUM> is selected from the group consisting of: a tube, a wire (e.g., a plurality of wires woven together), a shaft, a cable, a strand, and a fiber.

The elongate actuating element <NUM> may be rotated by the user, in which case the elongate actuating element <NUM> engages the threaded opening, such that rotation of the elongate actuating element <NUM> pulls a distal tip element <NUM> in the direction of the proximal base element <NUM> and causes shortening of the occlusion device <NUM>, thereby setting the distance between the distal tip element <NUM> and the proximal base element <NUM> and maintaining the set distance.

For some applications, the locking mechanism <NUM> is disposed at the proximal side 28A of the balloon <NUM>, for example, connected to or integrated into the proximal base element <NUM>.

After the desired distance has been set and the locking mechanism <NUM> has locked the locking elongate element <NUM>, the elongate actuating element <NUM> is released from the distal tip element <NUM>, and removed from the occlusion device <NUM> and the patient's body. For example, a distal portion <NUM> of the elongate actuating element <NUM> may comprise a first positive connection element, and the distal tip element <NUM> may be shaped so as to define a second positive connection element. The first positive connection element is releasably connected to the second positive connection element, such that the elongate actuating element <NUM> is releasably connected to the distal tip element <NUM>. The elongate actuating element <NUM> is released from the distal tip element <NUM> by decoupling the first positive connection element from the second positive connection element, such as by removing a retaining wire from within respective channels of the positive connection elements, as is known in the art.

As shown in <FIG>, in this configuration the elongate actuating element <NUM> is connected to the distal tip element <NUM> by being looped through a distal pulley system <NUM> such that first and second portions 542A and 542B of the elongate actuating element <NUM> extend distally through the proximal base element. Proximal pulling of one or both of the portions 542A and 542B sets the distance between the distal tip element <NUM> and the proximal base element <NUM>. The locking mechanism <NUM> comprises a locking mechanism <NUM>, e.g., which uses compression and/or friction to hold the elongate actuating element <NUM>, such as in a smaller channel of the locking mechanism <NUM>. Optionally, the locking mechanism <NUM> can be released after locking, in order to readjust the distance between the distal tip element <NUM> and the proximal base element <NUM>, and then locked again. Locking the locking mechanism <NUM> maintains the distance set between the distal tip element <NUM> and the proximal base element <NUM>. This arrangement allows both shortening of the distance and subsequent lengthening if necessary. The locking mechanism <NUM> is typically disposed at the proximal side 28A of the balloon <NUM>, for example, connected to or integrated into the proximal base element <NUM>.

Reference is now made to <FIG>, which shows a cross-sectional view of the occlusion device <NUM> illustrated in <FIG> in a compressed form thereof within the implant catheter <NUM> of the delivery system <NUM>, in accordance with an application of the present invention. Reference is also made to <FIG> and <FIG>, which show a perspective view and a cross-sectional view, respectively, of the occlusion device <NUM> illustrated in <FIG>, and of its main components, when released from the implant catheter <NUM> but still connected to the delivery system <NUM>. <FIG>show the occlusion device <NUM> by way of example; the delivery system <NUM> may also be used to deliver the other occlusion devices described herein, mutatis mutandis.

The implant catheter <NUM> allows the introduction of the occlusion device <NUM> through the cardiovascular system to a defect in the cardiovascular apparatus, to deploy the occlusion device <NUM> to seal the defect and maintain the occlusion, or the introduction of the occlusion device <NUM> to another location in the patient's body. Typically, the delivery system <NUM> further comprises a multiple-knobs delivery system handle <NUM>.

The implant catheter <NUM> is connected to the occlusion device <NUM> by a proximal connection element <NUM>. The implant catheter <NUM> contains the occlusion device <NUM> in its compressed form, i.e., its deflated and not expanded configuration. For some applications, when the occlusion device <NUM> is disposed in the implant catheter <NUM> in the compressed form, a greatest distance D between the proximal base element <NUM> and the distal tip element <NUM> is between <NUM> and <NUM>, such as between <NUM> and <NUM>. (The "greatest distance" is the distance between respective points of the proximal base element <NUM> and the distal tip element <NUM>, which points are farthest from each other. ) As mentioned above, <FIG> shows the occlusion device <NUM> by way of example; the delivery system <NUM> may also be used to deliver the other occlusion devices described herein, mutatis mutandis, in which case these other occlusion devices may optionally have the greatest distance D described immediately above.

The delivery system <NUM> comprises all the components and passages to allow controllable occlusion device <NUM> exposure, inflation, deflation, longitudinal adjustment, retrievability, and release at the end of the implantation. The implant catheter <NUM> is typically steerable, as is known in the catheter art. In another configuration, the implant catheter <NUM> is flexible instead of steerable.

Exposure of occlusion device <NUM> is controlled by an implant knob <NUM> in the delivery system handle <NUM>. For example, advancement of occlusion device <NUM> may be achieved by exposing and retrieving a connecting hypotube that is connected to the proximal base element <NUM>. Retrieval may be achieved by pulling a securing wire that is placed within the hypotube, so as to hold the securing wire in position within a positive connection. Proximal withdrawal of the securing wire frees the positive connection, thereby releasing the occlusion device <NUM>. For some applications, the handle <NUM> comprises a disk actuating knob <NUM>, which is arranged to move the elongate actuating element, to change the distance between the distal tip element <NUM> and the proximal base element <NUM>, such as by rotating and/or pulling/pushing the elongate actuating element, depending on the specific configuration of the elongate actuating element, as described hereinabove.

The delivery system <NUM> allows the course of the guidewire <NUM>, used to guide the occlusion device <NUM> to the targeted defect, and of the elongate actuating element, used to adjust the length of the occlusion device <NUM>, within the structure of the occlusion device and within the central lumen <NUM> of the occlusion device <NUM>.

Typically, the delivery system <NUM> includes mechanisms to inflate and deflate of the balloon <NUM> via an inflation port <NUM> in the handle <NUM>.

The delivery system <NUM> is configured to provide steering functionality in order to achieve good positioning of the occlusion device <NUM> in the targeted defect, for example controlled by a steering knob <NUM>, including a steering limiter, within the delivery system handle <NUM>. For cardiac applications, the steering functionality enables either an anterograde approach from the venous groin to the inferior vena cava, to the right atrium, to the left atrium, or a retrograde approach from the arterial groin to the left ventricle, and allows the occlusion device <NUM> implanted using any of the techniques known in the art.

Reference is made to <FIG>. For some applications, the frame <NUM>, <NUM>, or <NUM>, comprising the proximal base element <NUM> and the distal tip element <NUM> (e.g., the proximal and distal disks <NUM> and <NUM>) and the elongate actuating element <NUM>, struts <NUM>, or strut <NUM>, respectively, has plastic or metallic deformable characteristics, and may comprise any suitable biocompatible material including stainless steel, titanium, nitinol, tantalum, gold, platinum iridium, tungsten, alloys of any of the above-mentioned metals, including platinum-iridium alloys, cobalt-chromium alloys, nickel-titanium alloys and nickel-titanium-platinum alloys. Alternatively, the frame <NUM>, <NUM>, or <NUM> may comprise a polymer, including a polyester or polycarbonate copolymers, or any metal or polymer or combination of polymer(s) and metal(s) able to provide soft plastic deformation. Suitable materials include biodegradable materials that are also biocompatible, intending a material that undergoes breakdown or decomposition into non-significant compounds as part of a normal biological process. Suitable biodegradable materials include polylactic acid, polyglycolic acid (PGA), collagen or other connective proteins or natural materials, polycaprolactone, hyaluronic acid, adhesive proteins, co-polymers of these materials as well as composites and combinations thereof and combinations of other biodegradable polymers.

Reference is still made to <FIG>. The frame <NUM>, <NUM>, or <NUM> and the balloon <NUM> of the occlusion device <NUM>, <NUM>, or <NUM>, respectively, may be fabricated in different sizes, as necessary or appropriate for use in different sizes of cardiovascular defects or other suitable areas of the body.

Reference is made to <FIG> and to <FIG>, which show side views of the occlusion device <NUM> illustrated in <FIG> at different respective stages of expansion within a congenital defect (e.g., patent foramen ovale (PFO)). <FIG>show the occlusion device <NUM> by way of example; these techniques may also be used with the other occlusion devices described herein, mutatis mutandis.

A method of occluding a cardiovascular defect of a patient not forming part of the claimed invention is provided. Alternatively, the method may be used to seal a gap between a medical device and adjacent body tissue of a patient; for example, the medical device may be a prosthetic cardiac valve, and the method may treat paravalvular leak between the prosthetic cardiac valve and adjacent cardiac tissue of the patient.

The guidewire <NUM> is advanced into a body of the patient using delivery system <NUM>, such as shown in <FIG>. Using the delivery system <NUM>, compliant balloon <NUM> of the occlusion device <NUM> is positioned in a longitudinally extended form thereof (either partially or entirely compressed) in the cardiovascular defect, by advancing the occlusion device <NUM> over the guidewire <NUM>. Optionally, the balloon <NUM> is partially inflated before it is positioned in the longitudinally extended form thereof in the cardiovascular defect or the gap to be occluded. Alternatively, optionally, after the balloon <NUM> is positioned in the longitudinally extended form thereof in the cardiovascular defect or the gap to be occluded, the balloon <NUM> is partially inflated, and, thereafter, is repositioned in the longitudinally extended form thereof in the cardiovascular defect or the gap to be occluded.

The compliant balloon <NUM> is inflated by filling, via the inflation port <NUM> of the balloon <NUM>, a fluid into the fluid-tight balloon chamber <NUM> defined by the balloon <NUM>. <FIG> shows the occlusion device <NUM> after the balloon <NUM> has been inflated. The figure-eight shape shown in <FIG> may be achieved either because the defect constrains the balloon <NUM> to have the shape, and/or because the balloon <NUM> is configured to assume the shape even in the absence of the anatomy.

Thereafter, the balloon <NUM> is expanded in a radial or a lateral direction by shortening the distance between the distal tip element <NUM> and the proximal base element <NUM> to a desired distance and locking the distance. The radial or lateral expansion provides a good seal between the balloon and the adjacent anatomy. <FIG> shows the occlusion device <NUM> after the balloon <NUM> has been radially or laterally expanded.

Thereafter, the occlusion device <NUM> is released from the delivery system <NUM>.

For some applications, the proximal base element <NUM> and the distal tip element <NUM> are shaped so as to define the above-mentioned respective guidewire openings 105a and 105b substantially coaxial to the balloon lumen <NUM> for slidingly receiving therein the guidewire <NUM>, and advancing the occlusion device <NUM> over the guidewire <NUM> comprises sliding the guidewire <NUM> through the guidewire openings 105a and 105b described hereinabove.

For some applications, the balloon <NUM> has the above-mentioned balloon lumen <NUM> forming the above-mentioned longitudinal passage <NUM> from the proximal side 28A to the distal side 28B of the balloon <NUM>. The distance between the distal tip element <NUM> and the proximal base element <NUM> is shortened to the desired distance by pulling the elongate actuating element <NUM> disposed longitudinally slidable in the balloon lumen <NUM>, connected to the distal tip element <NUM>, and longitudinally moveable with respect to the proximal base element <NUM>. The distance is locked using locking mechanism <NUM> for maintaining, between the distal tip element <NUM> and the proximal base element <NUM>, the distance set using the elongate actuating element <NUM>.

For some applications, the occlusion device <NUM> is released from the delivery system <NUM> by releasing the above-mentioned proximal connection element <NUM> of the occlusion device <NUM> from the correspondingly configured distal connection element of the delivery system <NUM>.

Optionally, the balloon <NUM> is partially exposed, in its compressed form, from the implant catheter <NUM> of the delivery system <NUM> into the area to be treated (e.g., exposed for half of the length of the balloon <NUM>), and only the exposed portion of the balloon <NUM> is inflated. The balloon <NUM> is then repositioned for better occlusion targeting, and the balloon <NUM> is subsequently fully exposed from the delivery system <NUM>, and the remaining portion of the balloon <NUM> is inflated. Subsequently, the longitudinal distance is shortened.

Optionally, a portion of the balloon <NUM> is exposed, in its compressed form, from the implant catheter <NUM> of the delivery system <NUM> into the area to be treated (e.g., exposed for half of the length of the balloon <NUM>), and only the exposed portion of the balloon <NUM> is inflated. The exposed portion of the balloon <NUM> is expanded by shortening the distance between the distal tip element <NUM> and the proximal base element <NUM> by moving the distal tip element <NUM> toward the proximal base element <NUM>. Before the occlusion device <NUM> is released from the delivery system <NUM>, the remainder of the balloon <NUM> is exposed from the implant catheter, inflated, and expanded by further shortening the distance between the distal tip element <NUM> and the proximal base element <NUM>.

For some applications in which the method is used to treat paravalvular leak between a prosthetic cardiac valve and adjacent cardiac tissue of the patient, positioning and inflating the compliant balloon comprise positioning the balloon <NUM> in a ventricle of the patient; thereafter, partially inflating the balloon <NUM>; thereafter, disposing the balloon <NUM> approximately at a longitudinal center of the paravalvular leak; and thereafter, further inflating the balloon <NUM>. The balloon <NUM> is expanded after further inflating the balloon <NUM>. For some applications, the balloon <NUM> is disposed approximately at the longitudinal center of the paravalvular leak by proximally withdrawing the balloon <NUM> until the balloon <NUM> is disposed approximately at the longitudinal center of the paravalvular leak.

<FIG> show side views of the occlusion device <NUM> illustrated in <FIG> when expanded within a cavity or discontinuity of the body tissue. For example, the cavity or discontinuity may be a cardiovascular defect, such as a left atrial appendage (LAA). <FIG>show the occlusion device <NUM> by way of example; these techniques may also be used with the other occlusion devices described herein, mutatis mutandis. The deployment method described hereinabove with reference to <FIG> and <FIG> may be used to achieve the implantations shown in <FIG>, mutatis mutandis.

For some applications, the balloon <NUM> is configured to have a figure-eight shape (as shown in <FIG>), a pear shape (as shown in <FIG>, or a multilobed shape.

<FIG> show side views of the occlusion device <NUM> illustrated in <FIG> when expanded within a gap between a medical device and the adjacent body tissue, in accordance with an application of the present invention. For example, the medical device may comprise a stent, such as a stent of a prosthetic valve. <FIG> shows occlusion device <NUM> by way of example; these techniques may also be used with the other occlusion devices described herein, mutatis mutandis. The deployment method described hereinabove with reference to <FIG> and <FIG> may be used to achieve the implantation shown in <FIG>, mutatis mutandis.

In the configuration shown in <FIG>, the frame <NUM> of the occlusion device <NUM> comprises a backbone strut <NUM> that connects the proximal base element <NUM> and the distal tip element <NUM>, and is thicker than the other struts <NUM>, if provided. The backbone strut <NUM> is configured to reduce relative inflation on its lateral side of the balloon <NUM> compared to inflation of the balloon elsewhere, thereby providing a balloon shape that is appropriate for the anatomy of the gap to be filled. Alternatively or additionally, the wall of the balloon <NUM> on one lateral side may be thicker longitudinally on one lateral side, to create the backbone that causes the balloon to inflate less on that side.

Reference is now made to <FIG>, which shows a cross-sectional view of an expanded occlusion device <NUM>.

Reference is also made to <FIG>, which show side elevational views of the occlusion device <NUM> illustrated in <FIG>. Except as described below, occlusion device <NUM> may implement any of the features of the other occlusion devices described hereinabove (including, but not limited to occlusion devices <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, and <NUM>) or hereinbelow (including, but not limited to occlusion device <NUM>).

As shown in <FIG>, in this configuration the occlusion device <NUM> comprises a frame <NUM> that comprises a plurality of struts <NUM>, which may have any suitable form, passing inside (not shown) or outside (as shown) and tapering the balloon <NUM> component. Such an application may allow a cage-like structural confinement of the balloon <NUM> within its assembly, to avoid unnecessary interference of the occlusion device <NUM> with the body tissue or with implanted prostheses and to provide anchoring support of the occlusion device <NUM> within the defect, e.g., the cardiovascular defect. In this application, the frame <NUM> may comprise <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM> or any other suitable even or odd number of struts <NUM>. The struts <NUM> may be disposed inside or outside the balloon <NUM>. For some applications, the struts <NUM> are not fixed to any surfaces of the balloon <NUM>. For other applications, the struts <NUM> are (a) fixed to a surface (inner or outer) of the balloon <NUM>, (b) embedded in the wall of the balloon <NUM> during manufacture (such as by being cast within the wall). Alternatively, the balloon <NUM> may be molded over the struts <NUM>, which remain internally fixed to the balloon <NUM>.

In this configuration, the struts <NUM> are not arranged parallel with a central longitudinal axis <NUM> of the occlusion device <NUM>. For example, the struts <NUM> may be arranged in a generally helical configuration around the balloon <NUM>, such as shown.

Reference is also made to <FIG>, which show side elevational views of the occlusion device <NUM> illustrated in <FIG>. Except as described below, occlusion device <NUM> is identical to occlusion device <NUM>, described hereinabove with reference to <FIG> and may implement any of the features thereof or of the other occlusion devices described hereinabove (including, but not limited to occlusion devices <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, <NUM>, and <NUM>) or hereinbelow (including, but not limited to occlusion device <NUM>).

As shown in <FIG>, in this configuration the occlusion device <NUM> comprises a frame <NUM> that comprises a plurality of struts <NUM>, which may have any of the features of the frame <NUM> and/or the struts <NUM> described hereinabove with reference to <FIG>.

In this configuration, the struts <NUM> are not arranged parallel with a central longitudinal axis <NUM> of the occlusion device <NUM>. For example, the struts <NUM> may be arranged in a zig-zag configuration around the balloon <NUM>, optionally including partially helical portions, such as shown.

Reference is now made to <FIG>, which shows a method of deploying the occlusion device <NUM>.

<FIG> shows the occlusion device <NUM> by way of example; these techniques may also be used with the other occlusion devices described herein, mutatis mutandis. The first frame of <FIG> shows the delivery system <NUM> approaching the left atrial appendage defect. The second frame shows half of the occlusion device <NUM> exposed and pre-inflated. The third frame shows half of the occlusion device <NUM> adjusted. The fourth frame shows the other half of the occlusion device <NUM> exposed and pre-inflated. The fifth frame shows full inflation of the entire occlusion device <NUM>, and further adjustment that shortens the distance between the proximal base element <NUM> and the distal tip element <NUM>. The sixth (last) frame shows release of the occlusion device <NUM> at the target location.

Reference is now made to <FIG>, which shows a cross-sectional view of an expanded occlusion device <NUM> according to an application of the present invention. Reference is also made to <FIG>, which shows a side elevational view of the occlusion device <NUM> illustrated in <FIG>, in accordance with an application of the present invention. Except as described below, the occlusion device <NUM> may implement any of the features of the other occlusion devices described herein, mutatis mutandis, including, but not limited to, the struts of the frames described herein and the materials of the components of the occlusion devices. Like reference numerals refer to like parts.

The balloon <NUM> has the balloon lumen <NUM> forming the longitudinal passage <NUM> from the proximal side 28A to the distal side 28B of the balloon <NUM>. The elongate element <NUM> is disposed in the balloon lumen <NUM>. Typically, the proximal base element <NUM> and the distal tip element <NUM> are shaped so as to define respective guidewire openings 605a and 605b substantially coaxial to the balloon lumen <NUM> for slidingly receiving therein the guidewire <NUM>.

For some applications, the proximal base element <NUM> and the distal tip element <NUM> comprise a proximal disk <NUM> and the distal disk <NUM>, respectively.

For some applications, the occlusion device <NUM> further comprises at least one connecting strut fixed to the distal tip element and to the proximal base element, such as the single connecting strut <NUM> described hereinabove with reference to <FIG>, the single connecting strut <NUM> described hereinabove with reference to <FIG>, or the plurality of struts <NUM> described hereinabove with reference to <FIG>. The strut or struts may be disposed inside and/or outside the balloon <NUM>, and be arranged as described hereinabove.

A method of occluding a cardiovascular defect or a gap between a medical device and adjacent body tissue of a patient is provided. The method comprises:.

In some applications of the present invention, two or more occlusion devices are implanted to occlude a defect, either in series and/or alongside one another. For some applications, frames of the two or more occlusion devices are configured to connect the two or more occlusion devices together, typically in situ during an implantation procedure. For some applications, a portion of the surface of one of the balloons is bare of any of the frame, and the frame of another balloon is brought into contact with the bare portion of the other balloon, such as in order to avoid para-balloon leakage.

In some applications, the occlusion devices described herein are packaged in sterile packaging.

In any of the configurations described herein, the balloon <NUM> may optionally have an average wall thickness of between <NUM> and <NUM> microns, such as between <NUM> and <NUM> microns. Alternatively, the balloon <NUM> does not have this average wall thickness.

In any of the configurations described herein, the balloon <NUM> may optionally have, at a thinnest portion of a wall of the balloon <NUM>, a thinnest wall thickness of between <NUM> and <NUM> microns, such as between <NUM> and <NUM> microns. Alternatively, the balloon <NUM> does not have this thinnest wall thickness.

In any of the configurations described herein, the occlusion device may comprise a proximal radiopaque marker <NUM> that is fixed to the proximal base element and comprises a material that is more radiopaque than the proximal base element. Alternatively or additionally, in any of the configurations described herein, the occlusion device may comprise a distal radiopaque marker <NUM> that is fixed to the distal tip element and comprises a material that is more radiopaque than the distal tip element. These radiopaque markers enable the accurate positioning of the occlusion device echocardiographic, fluoroscopic, and/or x-ray guidance.

The proximal and distal radiopaque markers <NUM> and <NUM> are shown by way of example in <FIG>; these markers may also be provided in the other occlusion devices described herein. Alternatively, the occlusion devices described herein do not comprise proximal radiopaque marker <NUM> or distal radiopaque marker <NUM>. For example, each of the proximal radiopaque marker <NUM> and/or the distal radiopaque marker <NUM> may be shaped as a ring, such as shown in <FIG>; alternatively, the markers may have other shapes and/or different shapes or sizes from each other.

For example, the material of the proximal radiopaque marker <NUM> and/or the distal radiopaque marker <NUM> may comprise Au, PtIr, or Ta.

For example, the proximal radiopaque marker <NUM> and/or the distal radiopaque marker <NUM> may be fixed to the proximal base element and the distal tip element, respectively, by gluing, soldering, crimping, or welding.

In any of the configurations described herein, when the occlusion device is in a compressed, uninflated form, a greatest distance between the proximal base element <NUM> and the distal tip element <NUM> is between <NUM> and <NUM>, such as between <NUM> and <NUM>. (The "greatest distance" is the distance between respective points of the proximal base element <NUM> and the distal tip element <NUM>, which points are farthest from each other. ) Optionally, the occlusion device is in the above-mentioned compressed, uninflated form when the proximal connection element <NUM> is attached to the delivery system <NUM> and the occlusion device is not disposed in the implant catheter <NUM>.

Claim 1:
Apparatus for occluding a cardiovascular defect or a gap between a medical device and adjacent body tissue, the apparatus for use with a guidewire (<NUM>) and a delivery system (<NUM>), the apparatus comprising an occlusion device (<NUM>), which comprises:
a compliant balloon (<NUM>) defining a fluid-tight balloon chamber (<NUM>) and comprising an inflation port (<NUM>) for filling and unfilling a fluid into and from the balloon chamber (<NUM>);
a distal tip element (<NUM>) disposed at a distal side (28B) of the balloon (<NUM>), and a proximal base element (<NUM>) disposed at a proximal side (28A) of the balloon (<NUM>);
an elongate element (<NUM>) having a fixed length, and fixed to the distal tip element (<NUM>) and the proximal base element (<NUM>), the elongate element (<NUM>) being a wire or a cable; and
a proximal connection element (<NUM>) that is disposed at the proximal side (28A) of the balloon (<NUM>) and is configured to releasably connect the occlusion device (<NUM>) to a correspondingly configured distal connection element of the delivery system (<NUM>), characterised in that:
the elongate element (<NUM>) is fixed to the distal tip element (<NUM>) and the proximal base element (<NUM>) so as to set a fixed distance between the distal tip element (<NUM>) and the proximal base element (<NUM>),
the balloon (<NUM>) has a balloon lumen (<NUM>) forming a longitudinal passage (<NUM>) from the proximal side (28A) to the distal side (28B) of the balloon (<NUM>), and
the elongate element (<NUM>) is disposed in the balloon lumen (<NUM>).