Source: http://www.docstoc.com/docs/80716169/Tissue-Closure-System---Patent-7930016
Timestamp: 2014-07-11 15:16:03
Document Index: 185640874

Matched Legal Cases: ['Application No. 06734083', 'Application No. 06734083', 'Application No. 06734083', 'Application No. 07841754', 'Application No. 08746822', 'Application No. 08746822', 'Application No. 07812146', 'Application No. 07799466', 'art 150', 'art 150', 'art 162']

Tissue Closure System - Patent 7930016
United States Patent: 7930016
7,930,016
Tissue closure systems are described herein. Such a system may include a
deployment catheter and an attached imaging hood deployable into an
expanded configuration. In use, the imaging hood is placed against or
adjacent to a region of tissue to be imaged in a body lumen that is
normally filled with an opaque bodily fluid such as blood. A translucent
or transparent fluid, such as saline, can be pumped into the imaging hood
until the fluid displaces any blood, thereby leaving a clear region of
tissue to be imaged via an imaging element in the deployment catheter.
Additionally, the system can be deployed in a number of various ways to
effect the closure of wounds or openings in the patient body.
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This application claims the benefit of priority to U.S. Prov. Pat. App.
Ser. No. 60/737,521 filed Nov. 16, 2005 and is a continuation-in-part of
U.S. patent application Ser. No. 11/259,498 filed Oct. 25, 2005, which
claims priority to U.S. Prov. Pat. App. Ser. No. 60/649,246 filed Feb. 2,
2005, each of which is incorporated herein by reference in its entirety.
1.  A tissue closure system, comprising: a deployment catheter defining at least one lumen therethrough;  a hood comprising a non-inflatable membrane forming a fluid barrier
projecting distally from the deployment catheter and adapted to self-expand into an expanded deployed configuration defining an open area therein, wherein the open area is in fluid communication with the at least one lumen and with an environment
external to the hood through an opening defined by the hood;  a visualization element disposed within or adjacent to the open area of the hood for visualizing tissue adjacent to the open area;  and a tissue approximation assembly deployable from within
the hood and configured to secure a tissue opening.
2.  The system of claim 1 further comprising a delivery catheter through which the deployment catheter is deliverable.
3.  The system of claim 1 wherein the deployment catheter is steerable.
4.  The system of claim 3 wherein the deployment catheter is steered via at least one push-pull wire.
5.  The system of claim 3 wherein the deployment catheter is steered via computer control.
6.  The system of claim 1 wherein the hood is comprised of a compliant material.
7.  The system of claim 1 wherein the hood defines a contact edge for placement against a tissue surface.
8.  The system of claim 1 wherein the hood is adapted to be reconfigured from a low-profile delivery configuration to an expanded deployed configuration.
9.  The system of claim 8 wherein the hood comprises a frame of superelastic or shape memory alloy.
10.  The system of claim 1 wherein the visualization element comprises at least one optical fiber, CCD imagers, or CMOS imagers.
11.  The system of claim 1 wherein the visualization element is disposed within a distal end of the deployment catheter.
12.  The system of claim 1 wherein the visualization element is articulatable off-axis relative to a longitudinal axis of the deployment catheter.
13.  The system of claim 1 further comprising a pump for urging fluid into the hood.
14.  The system of claim 1 further comprising a cannula or needle defining a lumen through which the tissue approximation assembly is disposable.
15.  The system of claim 14 wherein the needle comprises a reconfigurable portion proximal to a piercing tip.
16.  The system of claim 1 wherein the tissue approximation assembly comprises a first and a second tissue anchor slidingly coupled to one another via a length of suture.
17.  The system of claim 1 wherein the tissue approximation assembly comprises a retaining wire having a reconfigurable distal portion.
18.  The system of claim 1 wherein the tissue approximation assembly comprises a patch mechanism having a ring with a patch supported thereby.
19.  The system of claim 18 wherein the ring comprises at least one tissue securing projection.
20.  The system of claim 18 further comprising a plurality of tissue securement members which are deployable through the patch and into an underlying tissue region.  Description
The present invention relates generally to medical devices used for visualizing and/or closing openings or defects within a body.  More particularly, the present invention relates to apparatus and methods for visualizing and/or closing openings
or wounds, e.g., septal defects, patent foramen ovale (PFO), etc., within a patient&#39;s body such as within the heart, which are generally difficult to image because of surrounding opaque bodily fluids such as blood.
Conventional devices for visualizing interior regions of a body lumen are known.  For example, ultrasound devices have been used to produce images from within a body in vivo.  Ultrasound has been used both with and without contrast agents, which
typically enhance ultrasound-derived images.
Other conventional methods have utilized catheters or probes having position sensors deployed within the body lumen, such as the interior of a cardiac chamber.  These types of positional sensors are typically used to determine the movement of a
cardiac tissue surface or the electrical activity within the cardiac tissue.  When a sufficient number of points have been sampled by the sensors, a &quot;map&quot; of the cardiac tissue may be generated.
Another conventional device utilizes an inflatable balloon which is typically introduced intravascularly in a deflated state and then inflated against the tissue region to be examined.  Imaging is typically accomplished by an optical fiber or
other apparatus such as electronic chips for viewing the tissue through the membrane(s) of the inflated balloon.  Moreover, the balloon must generally be inflated for imaging.  Other conventional balloons utilize a cavity or depression formed at a distal
end of the inflated balloon.  This cavity or depression is pressed against the tissue to be examined and is flushed with a clear fluid to provide a clear pathway through the blood.
However, such imaging balloons have many inherent disadvantages.  For instance, such balloons generally require that the balloon be inflated to a relatively large size which may undesirably displace surrounding tissue and interfere with fine
positioning of the imaging system against the tissue.  Moreover, the working area created by such inflatable balloons are generally cramped and limited in size.  Furthermore, inflated balloons may be susceptible to pressure changes in the surrounding
fluid.  For example, if the environment surrounding the inflated balloon undergoes pressure changes, e.g., during systolic and diastolic pressure cycles in a beating heart, the constant pressure change may affect the inflated balloon volume and its
positioning to produce unsteady or undesirable conditions for optimal tissue imaging.
Accordingly, these types of imaging modalities are generally unable to provide desirable images useful for sufficient diagnosis and therapy of the endoluminal structure, due in part to factors such as dynamic forces generated by the natural
movement of the heart.  Moreover, anatomic structures within the body can occlude or obstruct the image acquisition process.  Also, the presence and movement of opaque bodily fluids such as blood generally make in vivo imaging of tissue regions within
the heart difficult.
Other external imaging modalities are also conventionally utilized.  For example, computed tomography (CT) and magnetic resonance imaging (MRI) are typical modalities which are widely used to obtain images of body lumens such as the interior
chambers of the heart.  However, such imaging modalities fail to provide real-time imaging for intra-operative therapeutic procedures.  Fluoroscopic imaging, for instance, is widely used to identify anatomic landmarks within the heart and other regions
of the body.  However, fluoroscopy fails to provide an accurate image of the tissue quality or surface and also fails to provide for instrumentation for performing tissue manipulation or other therapeutic procedures upon the visualized tissue regions.
In addition, fluoroscopy provides a shadow of the intervening tissue onto a plate or sensor when it may be desirable to view the intraluminal surface of the tissue to diagnose pathologies or to perform some form of therapy on it.
Thus, a tissue imaging system which is able to provide real-time in vivo images of tissue regions within body lumens such as the heart through opaque media such as blood and which also provide instruments for therapeutic procedures upon the
visualized tissue are desirable.
A tissue imaging and manipulation apparatus that may be utilized for procedures within a body lumen, such as the heart, in which visualization of the surrounding tissue is made difficult, if not impossible, by medium contained within the lumen
such as blood, is described below.  Generally, such a tissue imaging and manipulation apparatus comprises an optional delivery catheter or sheath through which a deployment catheter and imaging hood may be advanced for placement against or adjacent to
the tissue to be imaged.
The deployment catheter may define a fluid delivery lumen therethrough as well as an imaging lumen within which an optical imaging fiber or assembly may be disposed for imaging tissue.  When deployed, the imaging hood may be expanded into any
number of shapes, e.g., cylindrical, conical as shown, semi-spherical, etc., provided that an open area or field is defined by the imaging hood.  The open area is the area within which the tissue region of interest may be imaged.  The imaging hood may
also define an atraumatic contact lip or edge for placement or abutment against the tissue region of interest.  Moreover, the distal end of the deployment catheter or separate manipulatable catheters may be articulated through various controlling
mechanisms such as push-pull wires manually or via computer control
The deployment catheter may also be stabilized relative to the tissue surface through various methods.  For instance, inflatable stabilizing balloons positioned along a length of the catheter may be utilized, or tissue engagement anchors may be
passed through or along the deployment catheter for temporary engagement of the underlying tissue.
In operation, after the imaging hood has been deployed, fluid may be pumped at a positive pressure through the fluid delivery lumen until the fluid fills the open area completely and displaces any blood from within the open area.  The fluid may
comprise any biocompatible fluid, e.g., saline, water, plasma, Fluorinert.TM., etc., which is sufficiently transparent to allow for relatively undistorted visualization through the fluid.  The fluid may be pumped continuously or intermittently to allow
for image capture by an optional processor which may be in communication with the assembly.
Moreover, the imaging assembly may be utilized to deploy one or more anchors into or through tissue regions for effecting the closure of openings or wounds such as atrial-septal defects or PFO.  Closure may be effected via a number of different
mechanisms and procedures.  In one variation, once the imaging hood has been desirably positioned proximate to the defect or PFO and visualized directly, a cannula or piercing needle may be advanced through the deployment catheter and through the imaging
hood.  One or more tissue anchors may then be deployed either through the cannula or needle to approximate and secure the tissue opening.  Alternatively, a patching mechanism may be utilized for securement over the opening via barbs, projections, etc.,
or via any number of expandable securement devices which may be passed through the opening and expanded on a distal side of the opening to urge the patch against the tissue.
FIGS. 10A and 10B show charts illustrating how fluid pressure within the imaging hood may be coordinated with the surrounding blood pressure; the fluid pressure in the imaging hood may be coordinated with the blood pressure or it may be
regulated based upon pressure feedback from the blood.
FIGS. 12A to 12G illustrate a reconfigurable needle which may be deployed through a cannula, while under direct visualization, through one or more layers of tissue surrounding the tissue opening and deployment of tissue anchors to approximate
and secure the opening.
FIG. 23 shows a partial cross-sectional view of a heart with another variation of a patch device which utilizes support ring, patch material and a securement member which is reconfigurable from a low-profile configuration into an expanded
A tissue-imaging and manipulation apparatus described below is able to provide real-time images in vivo of tissue regions within a body lumen such as a heart, which is filled with blood flowing dynamically therethrough and is also able to
provide intravascular tools and instruments for performing various procedures upon the imaged tissue regions.  Such an apparatus may be utilized for many procedures, e.g., facilitating trans-septal access to the left atrium, cannulating the coronary
sinus, diagnosis of valve regurgitation/stenosis, valvuloplasty, atrial appendage closure, arrhythmogenic focus ablation, among other procedures.
One variation of a tissue access and imaging apparatus is shown in the detail perspective views of FIGS. 1A to 1C.  As shown in FIG. 1A, tissue imaging and manipulation assembly 10 may be delivered intravascularly through the patient&#39;s body in a
low-profile configuration via a delivery catheter or sheath 14.  In the case of treating tissue, such as the mitral valve located at the outflow tract of the left atrium of the heart, it is generally desirable to enter or access the left atrium while
minimizing trauma to the patient.  To non-operatively effect such access, one conventional approach involves puncturing the intra-atrial septum from the right atrial chamber to the left atrial chamber in a procedure commonly called a trans-septal
procedure or septostomy.  For procedures such as percutaneous valve repair and replacement, trans-septal access to the left atrial chamber of the heart may allow for larger devices to be introduced into the venous system than can generally be introduced
percutaneously into the arterial system.
When the imaging and manipulation assembly 10 is ready to be utilized for imaging tissue, imaging hood 12 may be advanced relative to catheter 14 and deployed from a distal opening of catheter 14, as shown by the arrow.  Upon deployment, imaging
hood 12 may be unconstrained to expand or open into a deployed imaging configuration, as shown in FIG. 1B.  Imaging hood 12 may be fabricated from a variety of pliable or conformable biocompatible material including but not limited to, e.g., polymeric,
plastic, or woven materials.  One example of a woven material is Kevlar.RTM.  (E.I.  du Pont de Nemours, Wilmington, Del.), which is an aramid and which can be made into thin, e.g., less than 0.001 in., materials which maintain enough integrity for such
applications described herein.  Moreover, the imaging hood 12 may be fabricated from a translucent or opaque material and in a variety of different colors to optimize or attenuate any reflected lighting from surrounding fluids or structures, i.e.,
anatomical or mechanical structures or instruments.  In either case, imaging hood 12 may be fabricated into a uniform structure or a scaffold-supported structure, in which case a scaffold made of a shape memory alloy, such as Nitinol, or a spring steel,
or plastic, etc., may be fabricated and covered with the polymeric, plastic, or woven material.
Imaging hood 12 may be attached at interface 24 to a deployment catheter 16 which may be translated independently of deployment catheter or sheath 14.  Attachment of interface 24 may be accomplished through any number of conventional methods.
Deployment catheter 16 may define a fluid delivery lumen 18 as well as an imaging lumen 20 within which an optical imaging fiber or assembly may be disposed for imaging tissue.  When deployed, imaging hood 12 may expand into any number of shapes, e.g.,
cylindrical, conical as shown, semi-spherical, etc., provided that an open area or field 26 is defined by imaging hood 12.  The open area 26 is the area within which the tissue region of interest may be imaged.  Imaging hood 12 may also define an
atraumatic contact lip or edge 22 for placement or abutment against the tissue region of interest.  Moreover, the diameter of imaging hood 12 at its maximum fully deployed diameter, e.g., at contact lip or edge 22, is typically greater relative to a
diameter of the deployment catheter 16 (although a diameter of contact lip or edge 22 may be made to have a smaller or equal diameter of deployment catheter 16).  For instance, the contact edge diameter may range anywhere from 1 to 5 times (or even
greater, as practicable) a diameter of deployment catheter 16.  FIG. 1C shows an end view of the imaging hood 12 in its deployed configuration.  Also shown are the contact lip or edge 22 and fluid delivery lumen 18 and imaging lumen 20.
The imaging and manipulation assembly 10 may additionally define a guidewire lumen therethrough, e.g., a concentric or eccentric lumen, as shown in the side and end views, respectively, of FIGS. 1D to 1F.  The deployment catheter 16 may define
guidewire lumen 19 for facilitating the passage of the system over or along a guidewire 17, which may be advanced intravascularly within a body lumen.  The deployment catheter 16 may then be advanced over the guidewire 17, as generally known in the art.
In operation, after imaging hood 12 has been deployed, as in FIG. 1B, and desirably positioned against the tissue region to be imaged along contact edge 22, the displacing fluid may be pumped at positive pressure through fluid delivery lumen 18
until the fluid fills open area 26 completely and displaces any fluid 28 from within open area 26.  The displacing fluid flow may be laminarized to improve its clearing effect and to help prevent blood from re-entering the imaging hood 12.
Alternatively, fluid flow may be started before the deployment takes place.  The displacing fluid, also described herein as imaging fluid, may comprise any biocompatible fluid, e.g., saline, water, plasma, etc., which is sufficiently transparent to allow
for relatively undistorted visualization through the fluid.  Alternatively or additionally, any number of therapeutic drugs may be suspended within the fluid or may comprise the fluid itself which is pumped into open area 26 and which is subsequently
passed into and through the heart and the patient body.
As seen in the example of FIGS. 2A and 2B, deployment catheter 16 may be manipulated to position deployed imaging hood 12 against or near the underlying tissue region of interest to be imaged, in this example a portion of annulus A of mitral
valve MV within the left atrial chamber.  As the surrounding blood 30 flows around imaging hood 12 and within open area 26 defined within imaging hood 12, as seen in FIG. 2A, the underlying annulus A is obstructed by the opaque blood 30 and is difficult
to view through the imaging lumen 20.  The translucent fluid 28, such as saline, may then be pumped through fluid delivery lumen 18, intermittently or continuously, until the blood 30 is at least partially, and preferably completely, displaced from
within open area 26 by fluid 28, as shown in FIG. 2B.
Although contact edge 22 need not directly contact the underlying tissue, it is at least preferably brought into close proximity to the tissue such that the flow of clear fluid 28 from open area 26 may be maintained to inhibit significant
backflow of blood 30 back into open area 26.  Contact edge 22 may also be made of a soft elastomeric material such as certain soft grades of silicone or polyurethane, as typically known, to help contact edge 22 conform to an uneven or rough underlying
anatomical tissue surface.  Once the blood 30 has been displaced from imaging hood 12, an image may then be viewed of the underlying tissue through the clear fluid 30.  This image may then be recorded or available for real-time viewing for performing a
therapeutic procedure.  The positive flow of fluid 28 may be maintained continuously to provide for clear viewing of the underlying tissue.  Alternatively, the fluid 28 may be pumped temporarily or sporadically only until a clear view of the tissue is
available to be imaged and recorded, at which point the fluid flow 28 may cease and blood 30 may be allowed to seep or flow back into imaging hood 12.  This process may be repeated a number of times at the same tissue region or at multiple tissue
In desirably positioning the assembly at various regions within the patient body, a number of articulation and manipulation controls may be utilized.  For example, as shown in the articulatable imaging assembly 40 in FIG. 3A, one or more
push-pull wires 42 may be routed through deployment catheter 16 for steering the distal end portion of the device in various directions 46 to desirably position the imaging hood 12 adjacent to a region of tissue to be visualized.  Depending upon the
positioning and the number of push-pull wires 42 utilized, deployment catheter 16 and imaging hood 12 may be articulated into any number of configurations 44.  The push-pull wire or wires 42 may be articulated via their proximal ends from outside the
patient body manually utilizing one or more controls.  Alternatively, deployment catheter 16 may be articulated by computer control, as further described below.
Additionally or alternatively, an articulatable delivery catheter 48, which may be articulated via one or more push-pull wires and having an imaging lumen and one or more working lumens, may be delivered through the deployment catheter 16 and
into imaging hood 12.  With a distal portion of articulatable delivery catheter 48 within imaging hood 12, the clear displacing fluid may be pumped through delivery catheter 48 or deployment catheter 16 to clear the field within imaging hood 12.  As
shown in FIG. 3B, the articulatable delivery catheter 48 may be articulated within the imaging hood to obtain a better image of tissue adjacent to the imaging hood 12.  Moreover, articulatable delivery catheter 48 may be articulated to direct an
instrument or tool passed through the catheter 48, as described in detail below, to specific areas of tissue imaged through imaging hood 12 without having to reposition deployment catheter 16 and re-clear the imaging field within hood 12.
Alternatively, rather than passing an articulatable delivery catheter 48 through the deployment catheter 16, a distal portion of the deployment catheter 16 itself may comprise a distal end 49 which is articulatable within imaging hood 12, as
shown in FIG. 3C.  Directed imaging, instrument delivery, etc., may be accomplished directly through one or more lumens within deployment catheter 16 to specific regions of the underlying tissue imaged within imaging hood 12.
Visualization within the imaging hood 12 may be accomplished through an imaging lumen 20 defined through deployment catheter 16, as described above.  In such a configuration, visualization is available in a straight-line manner, i.e., images are
generated from the field distally along a longitudinal axis defined by the deployment catheter 16.  Alternatively or additionally, an articulatable imaging assembly having a pivotable support member 50 may be connected to, mounted to, or otherwise passed
through deployment catheter 16 to provide for visualization off-axis relative to the longitudinal axis defined by deployment catheter 16, as shown in FIG. 4A.  Support member 50 may have an imaging element 52, e.g., a CCD or CMOS imager or optical fiber,
attached at its distal end with its proximal end connected to deployment catheter 16 via a pivoting connection 54.
If one or more optical fibers are utilized for imaging, the optical fibers 58 may be passed through deployment catheter 16, as shown in the cross-section of FIG. 4B, and routed through the support member 50.  The use of optical fibers 58 may
provide for increased diameter sizes of the one or several lumens 56 through deployment catheter 16 for the passage of diagnostic and/or therapeutic tools therethrough.  Alternatively, electronic chips, such as a charge coupled device (CCD) or a CMOS
imager, which are typically known, may be utilized in place of the optical fibers 58, in which case the electronic imager may be positioned in the distal portion of the deployment catheter 16 with electric wires being routed proximally through the
deployment catheter 16.  Alternatively, the electronic imagers may be wirelessly coupled to a receiver for the wireless transmission of images.  Additional optical fibers or light emitting diodes (LEDs) can be used to provide lighting for the image or
operative theater, as described below in further detail.  Support member 50 may be pivoted via connection 54 such that the member 50 can be positioned in a low-profile configuration within channel or groove 60 defined in a distal portion of catheter 16,
as shown in the cross-section of FIG. 4C.  During intravascular delivery of deployment catheter 16 through the patient body, support member 50 can be positioned within channel or groove 60 with imaging hood 12 also in its low-profile configuration.
During visualization, imaging hood 12 may be expanded into its deployed configuration and support member 50 may be deployed into its off-axis configuration for imaging the tissue adjacent to hood 12, as in FIG. 4A.  Other configurations for support
member 50 for off-axis visualization may be utilized, as desired.
FIG. 5 shows an illustrative cross-sectional view of a heart H having tissue regions of interest being viewed via an imaging assembly 10.  In this example, delivery catheter assembly 70 may be introduced percutaneously into the patient&#39;s
vasculature and advanced through the superior vena cava SVC and into the right atrium RA.  The delivery catheter or sheath 72 may be articulated through the atrial septum AS and into the left atrium LA for viewing or treating the tissue, e.g., the
annulus A, surrounding the mitral valve MV.  As shown, deployment catheter 16 and imaging hood 12 may be advanced out of delivery catheter 72 and brought into contact or in proximity to the tissue region of interest.  In other examples, delivery catheter
assembly 70 may be advanced through the inferior vena cava IVC, if so desired.  Moreover, other regions of the heart H, e.g., the right ventricle RV or left ventricle LV, may also be accessed and imaged or treated by imaging assembly 10.
In accessing regions of the heart H or other parts of the body, the delivery catheter or sheath 14 may comprise a conventional intra-vascular catheter or an endoluminal delivery device.  Alternatively, robotically-controlled delivery catheters
may also be optionally utilized with the imaging assembly described herein, in which case a computer-controller 74 may be used to control the articulation and positioning of the delivery catheter 14.  An example of a robotically-controlled delivery
catheter which may be utilized is described in further detail in US Pat.  Pub.  2002/0087169 A1 to Brock et al. entitled &quot;Flexible Instrument&quot;, which is incorporated herein by reference in its entirety.  Other robotically-controlled delivery catheters
manufactured by Hansen Medical, Inc.  (Mountain View, Calif.) may also be utilized with the delivery catheter 14.
To facilitate stabilization of the deployment catheter 16 during a procedure, one or more inflatable balloons or anchors 76 may be positioned along the length of catheter 16, as shown in FIG. 6A.  For example, when utilizing a trans-septal
approach across the atrial septum AS into the left atrium LA, the inflatable balloons 76 may be inflated from a low-profile into their expanded configuration to temporarily anchor or stabilize the catheter 16 position relative to the heart H. FIG. 6B
shows a first balloon 78 inflated while FIG. 6C also shows a second balloon 80 inflated proximal to the first balloon 78.  In such a configuration, the septal wall AS may be wedged or sandwiched between the balloons 78, 80 to temporarily stabilize the
catheter 16 and imaging hood 12.  A single balloon 78 or both balloons 78, 80 may be used.  Other alternatives may utilize expandable mesh members, malecots, or any other temporary expandable structure.  After a procedure has been accomplished, the
balloon assembly 76 may be deflated or re-configured into a low-profile for removal of the deployment catheter 16.
To further stabilize a position of the imaging hood 12 relative to a tissue surface to be imaged, various anchoring mechanisms may be optionally employed for temporarily holding the imaging hood 12 against the tissue.  Such anchoring mechanisms
may be particularly useful for imaging tissue which is subject to movement, e.g., when imaging tissue within the chambers of a beating heart.  A tool delivery catheter 82 having at least one instrument lumen and an optional visualization lumen may be
delivered through deployment catheter 16 and into an expanded imaging hood 12.  As the imaging hood 12 is brought into contact against a tissue surface T to be examined, an anchoring mechanisms such as a helical tissue piercing device 84 may be passed
through the tool delivery catheter 82, as shown in FIG. 7A, and into imaging hood 12.
The helical tissue engaging device 84 may be torqued from its proximal end outside the patient body to temporarily anchor itself into the underlying tissue surface T. Once embedded within the tissue T, the helical tissue engaging device 84 may
be pulled proximally relative to deployment catheter 16 while the deployment catheter 16 and imaging hood 12 are pushed distally, as indicated by the arrows in FIG. 7B, to gently force the contact edge or lip 22 of imaging hood against the tissue T. The
positioning of the tissue engaging device 84 may be locked temporarily relative to the deployment catheter 16 to ensure secure positioning of the imaging hood 12 during a diagnostic or therapeutic procedure within the imaging hood 12.  After a procedure,
tissue engaging device 84 may be disengaged from the tissue by torquing its proximal end in the opposite direction to remove the anchor form the tissue T and the deployment catheter 16 may be repositioned to another region of tissue where the anchoring
process may be repeated or removed from the patient body.  The tissue engaging device 84 may also be constructed from other known tissue engaging devices such as vacuum-assisted engagement or grasper-assisted engagement tools, among others.
Although a helical anchor 84 is shown, this is intended to be illustrative and other types of temporary anchors may be utilized, e.g., hooked or barbed anchors, graspers, etc. Moreover, the tool delivery catheter 82 may be omitted entirely and
the anchoring device may be delivered directly through a lumen defined through the deployment catheter 16.
In another variation where the tool delivery catheter 82 may be omitted entirely to temporarily anchor imaging hood 12, FIG. 7C shows an imaging hood 12 having one or more tubular support members 86, e.g., four support members 86 as shown,
integrated with the imaging hood 12.  The tubular support members 86 may define lumens therethrough each having helical tissue engaging devices 88 positioned within.  When an expanded imaging hood 12 is to be temporarily anchored to the tissue, the
helical tissue engaging devices 88 may be urged distally to extend from imaging hood 12 and each may be torqued from its proximal end to engage the underlying tissue T. Each of the helical tissue engaging devices 88 may be advanced through the length of
deployment catheter 16 or they may be positioned within tubular support members 86 during the delivery and deployment of imaging hood 12.  Once the procedure within imaging hood 12 is finished, each of the tissue engaging devices 88 may be disengaged
from the tissue and the imaging hood 12 may be repositioned to another region of tissue or removed from the patient body.
An illustrative example is shown in FIG. 8A of a tissue imaging assembly connected to a fluid delivery system 90 and to an optional processor 98 and image recorder and/or viewer 100.  The fluid delivery system 90 may generally comprise a pump 92
and an optional valve 94 for controlling the flow rate of the fluid into the system.  A fluid reservoir 96, fluidly connected to pump 92, may hold the fluid to be pumped through imaging hood 12.  An optional central processing unit or processor 98 may be
in electrical communication with fluid delivery system 90 for controlling flow parameters such as the flow rate and/or velocity of the pumped fluid.  The processor 98 may also be in electrical communication with an image recorder and/or viewer 100 for
directly viewing the images of tissue received from within imaging hood 12.  Imager recorder and/or viewer 100 may also be used not only to record the image but also the location of the viewed tissue region, if so desired.
Optionally, processor 98 may also be utilized to coordinate the fluid flow and the image capture.  For instance, processor 98 may be programmed to provide for fluid flow from reservoir 96 until the tissue area has been displaced of blood to
obtain a clear image.  Once the image has been determined to be sufficiently clear, either visually by a practitioner or by computer, an image of the tissue may be captured automatically by recorder 100 and pump 92 may be automatically stopped or slowed
by processor 98 to cease the fluid flow into the patient.  Other variations for fluid delivery and image capture are, of course, possible and the aforementioned configuration is intended only to be illustrative and not limiting.
FIG. 8B shows a further illustration of a hand-held variation of the fluid delivery and tissue manipulation system 110.  In this variation, system 110 may have a housing or handle assembly 112 which can be held or manipulated by the physician
from outside the patient body.  The fluid reservoir 114, shown in this variation as a syringe, can be fluidly coupled to the handle assembly 112 and actuated via a pumping mechanism 116, e.g., lead screw.  Fluid reservoir 114 may be a simple reservoir
separated from the handle assembly 112 and fluidly coupled to handle assembly 112 via one or more tubes.  The fluid flow rate and other mechanisms may be metered by the electronic controller 118.
Deployment of imaging hood 12 may be actuated by a hood deployment switch 120 located on the handle assembly 112 while dispensation of the fluid from reservoir 114 may be actuated by a fluid deployment switch 122, which can be electrically
coupled to the controller 118.  Controller 118 may also be electrically coupled to a wired or wireless antenna 124 optionally integrated with the handle assembly 112, as shown in the figure.  The wireless antenna 124 can be used to wirelessly transmit
images captured from the imaging hood 12 to a receiver, e.g., via Bluetooth.RTM.  wireless technology (Bluetooth SIG, Inc., Bellevue, Wash.), RF, etc., for viewing on a monitor 128 or for recording for later viewing.
Articulation control of the deployment catheter 16, or a delivery catheter or sheath 14 through which the deployment catheter 16 may be delivered, may be accomplished by computer control, as described above, in which case an additional
controller may be utilized with handle assembly 112.  In the case of manual articulation, handle assembly 112 may incorporate one or more articulation controls 126 for manual manipulation of the position of deployment catheter 16.  Handle assembly 112
may also define one or more instrument ports 130 through which a number of intravascular tools may be passed for tissue manipulation and treatment within imaging hood 12, as described further below.  Furthermore, in certain procedures, fluid or debris
may be sucked into imaging hood 12 for evacuation from the patient body by optionally fluidly coupling a suction pump 132 to handle assembly 112 or directly to deployment catheter 16.
As described above, fluid may be pumped continuously into imaging hood 12 to provide for clear viewing of the underlying tissue.  Alternatively, fluid may be pumped temporarily or sporadically only until a clear view of the tissue is available
to be imaged and recorded, at which point the fluid flow may cease and the blood may be allowed to seep or flow back into imaging hood 12.  FIGS. 9A to 9C illustrate an example of capturing several images of the tissue at multiple regions.  Deployment
catheter 16 may be desirably positioned and imaging hood 12 deployed and brought into position against a region of tissue to be imaged, in this example the tissue surrounding a mitral valve MV within the left atrium of a patient&#39;s heart.  The imaging
hood 12 may be optionally anchored to the tissue, as described above, and then cleared by pumping the imaging fluid into the hood 12.  Once sufficiently clear, the tissue may be visualized and the image captured by control electronics 118.  The first
captured image 140 may be stored and/or transmitted wirelessly 124 to a monitor 128 for viewing by the physician, as shown in FIG. 9A.
The deployment catheter 16 may be then repositioned to an adjacent portion of mitral valve MV, as shown in FIG. 9B, where the process may be repeated to capture a second image 142 for viewing and/or recording.  The deployment catheter 16 may
again be repositioned to another region of tissue, as shown in FIG. 9C, where a third image 144 may be captured for viewing and/or recording.  This procedure may be repeated as many times as necessary for capturing a comprehensive image of the tissue
surrounding mitral valve MV, or any other tissue region.  When the deployment catheter 16 and imaging hood 12 is repositioned from tissue region to tissue region, the pump may be stopped during positioning and blood or surrounding fluid may be allowed to
enter within imaging hood 12 until the tissue is to be imaged, where the imaging hood 12 may be cleared, as above.
As mentioned above, when the imaging hood 12 is cleared by pumping the imaging fluid within for clearing the blood or other bodily fluid, the fluid may be pumped continuously to maintain the imaging fluid within the hood 12 at a positive
pressure or it may be pumped under computer control for slowing or stopping the fluid flow into the hood 12 upon detection of various parameters or until a clear image of the underlying tissue is obtained.  The control electronics 118 may also be
programmed to coordinate the fluid flow into the imaging hood 12 with various physical parameters to maintain a clear image within imaging hood 12.
One example is shown in FIG. 10A which shows a chart 150 illustrating how fluid pressure within the imaging hood 12 may be coordinated with the surrounding blood pressure.  Chart 150 shows the cyclical blood pressure 156 alternating between
diastolic pressure 152 and systolic pressure 154 over time T due to the beating motion of the patient heart.  The fluid pressure of the imaging fluid, indicated by plot 160, within imaging hood 12 may be automatically timed to correspond to the blood
pressure changes 160 such that an increased pressure is maintained within imaging hood 12 which is consistently above the blood pressure 156 by a slight increase .DELTA.P, as illustrated by the pressure difference at the peak systolic pressure 158.  This
pressure difference, .DELTA.P, may be maintained within imaging hood 12 over the pressure variance of the surrounding blood pressure to maintain a positive imaging fluid pressure within imaging hood 12 to maintain a clear view of the underlying tissue.
One benefit of maintaining a constant .DELTA.P is a constant flow and maintenance of a clear field.
FIG. 10B shows a chart 162 illustrating another variation for maintaining a clear view of the underlying tissue where one or more sensors within the imaging hood 12, as described in further detail below, may be configured to sense pressure
changes within the imaging hood 12 and to correspondingly increase the imaging fluid pressure within imaging hood 12.  This may result in a time delay, .DELTA.T, as illustrated by the shifted fluid pressure 160 relative to the cycling blood pressure 156,
although the time delay .DELTA.T may be negligible in maintaining the clear image of the underlying tissue.  Predictive software algorithms can also be used to substantially eliminate this time delay by predicting when the next pressure wave peak will
arrive and by increasing the pressure ahead of the pressure wave&#39;s arrival by an amount of time equal to the aforementioned time delay to essentially cancel the time delay out.
The variations in fluid pressure within imaging hood 12 may be accomplished in part due to the nature of imaging hood 12.  An inflatable balloon, which is conventionally utilized for imaging tissue, may be affected by the surrounding blood
pressure changes.  On the other hand, an imaging hood 12 retains a constant volume therewithin and is structurally unaffected by the surrounding blood pressure changes, thus allowing for pressure increases therewithin.  The material that hood 12 is made
from may also contribute to the manner in which the pressure is modulated within this hood 12.  A stiffer hood material, such as high durometer polyurethane or Nylon, may facilitate the maintaining of an open hood when deployed.  On the other hand, a
relatively lower durometer or softer material, such as a low durometer PVC or polyurethane, may collapse from the surrounding fluid pressure and may not adequately maintain a deployed or expanded hood.
With the imaging hood 12, any number of intravascular procedures may be performed especially while under direct visualization, including the closure or apposition of tissue wounds or openings.  Turning now to the side view of FIG. 11A,
deployment catheter 16 and imaging hood 12 may be directed, in one example of use, to intravascularly closing a coronary defect such as an atrial septal defect (ASD) or a patent foramen ovale (PFO) 170.  The tissue defect, in this example PFO 170, is
formed along the atrial septum AS between the septum primum SP and septum secundum SS and defines an opening 172 which allows blood to be shunted between the left and right atrial chambers.  With deployment catheter 16 advanced intravascularly into the
left or right atrial chamber, hood 12 may be articulated or directed via catheter 16 into contact with a portion of the atrial septum AS adjacent or proximate to the opening 172.
Once desirably positioned, hood 12 may be optionally purged of blood or fluids to allow for direct visualization of the underlying tissue through hood 12 and cannula 174 may be advanced through one of the working lumens into contact against the
tissue, as shown in FIG. 11B.  A piercing needle 176 having a needle lumen 178 may be advanced distally through cannula 174 until the needle tip pierces through the atrial septum AS, as shown in FIG. 12A.  (Hood 12 is omitted for the sake of clarity.)
Needle 176 may be formed of a shape memory alloy or other pre-formed metal, as described above, such that the needle 176 defines a portion 180 proximal to the needle tip which is biased to curve or is curvable upon being unconstrained from the cannula
174, as illustrated in FIG. 12B.  As the needle 176 is further advanced, curved portion 180 may be free to curve into an arcuate or retro-flexed configuration such that the piercing tip of the needle may be pulled proximally to pierce back through the
tissue, e.g., through the septum secundum SS and septum primum SP, until the tip reappears on the same side of the chamber as cannula 174, as illustrated in FIG. 12C.  Once needle lumen 178 has cleared the tissue, a first anchor 182 connected via a
length of suture 186 may be deployed from needle 176.  With first anchor 182 deployed, needle 176 may be withdrawn proximally back through the tissue layers leaving first anchor 182 to rest against the tissue surface while remaining coupled or connected
to suture 186, as illustrated in FIG. 12D.
Needle 176 may be further withdrawn back into cannula 174 such that needle 176 is pulled back through the tissue, where a second anchor 184 coupled or connected to suture 186 may be ejected or urged from needle lumen 178, as illustrated in FIG.
12E.  As needle 176 is pulled proximally back into cannula 174, it may be straightened back into its delivery configuration.  With both anchors 182, 184 ejected from needle 176 and connected to one another via suture 186 routed through the tissue layers
forming opening 172 of PFO 170, the anchors 182, 184 may be urged towards one another to cinch the PFO 170 closed and a locking mechanism 188 may be passed along the suture 186 proximal to second anchor 188 to ensure that suture 186 remains tensioned
between anchors 182, 184, as shown in FIG. 12F.  With PFO 170 cinched shut, suture 186 proximal to locking mechanism 188 may be cut or otherwise released to leave anchors 182, 184 and suture 186 behind, as illustrated in FIG. 12G.
Alternative mechanisms for releasing anchors through tissue are shown and described in further detail in U.S.  Pat.  Pub.  No. 2005/0059984 A1 to Chanduszko et al. and further examples of locking mechanisms which may be utilized herein are also
described in U.S.  Pat.  Pub.  No. 2003/0018358 A1 to Saadat, each of which are incorporated herein by reference in its entirety.
In another variation for closing a PFO or other tissue opening is shown in FIGS. 13A to 13E.  As above, deployment catheter 16 and hood 12 may be articulated into position over tissue opening 172, where cannula 174 may be advanced distally
within hood 12 into contact against the underlying tissue, as shown in FIG. 13A.  FIG. 13B illustrates a detail view of cannula 174 against the underlying tissue with the hood omitted for the sake of clarity.  A retaining wire 190 having a piercing tip
and made from a shape memory alloy or other metal, as described above, may be advanced distally through the cannula lumen until it pierces through the tissue layers SP, SS surrounding opening 172.  Once free from the constraints of cannula 174, the
distal portion 192 of retaining wire 190, which may be preformed or biased to expand or reconfigure itself into an enlarged retaining configuration, may begin to expand, as shown in FIG. 13C.
As retaining wire 190 is further urged distally through the tissue, pre-formed portion 192 may fully reconfigure itself in a shape which resists being pulled proximally through the tissue, as shown in FIG. 13D.  With this configuration,
retaining wire 190 may be pulled proximally through cannula 174, as indicated by the arrow, to approximate the tissue layers towards one another and close the opening 172 of PFO 170, as shown in FIG. 13E.  Once the tissue opening has been closed,
retaining wire 190 may be detached and secured in place or further procedures may be performed upon the tissue to otherwise secure the closed opening, in which case wire 190 may be then withdrawn into cannula 174 and back into its straightened
configuration for withdrawal from the patient body.
In yet another variation, deployment catheter 16 and hood 12 may be articulated or otherwise guided into position or proximity to opening 172 and piercing needle 200 may be advanced through hood 12 while under direct visualization through the
purged hood 12, as shown in FIG. 14A.  Needle 200 may be pierced through the layers SP, SS of the opening 172 until piercing tip 202 has cleared the tissue and is within the adjacent chamber.  Retaining wire 190 may then be advanced through needle lumen
204 until the pre-formed portion 192 has been deployed from lumen 204 and expanded, as shown in FIG. 14B.  Needle 200 may then be withdrawn proximally through the tissue until piercing tip 202 has cleared the tissue.  Retaining wire 190 may then be urged
proximally, as indicated by the arrow, to approximate the tissue surrounding the opening 172 and portion 192 may be left in place or another procedure may be performed upon the tissue to maintain closure of the opening, as above and as shown in FIG. 14C.
In yet another variation, with deployment catheter 16 and hood 12 urged into position proximate to opening 172, piercing needle 200 may be urged through the tissue layers until piercing tip 202 has pierced through and cleared the tissue, as
described above and as shown in FIG. 15A.  Once needle 200 is in its desired position, first anchor 182 connected via suture 186, may be urged through needle lumen 204 and ejected, as shown in FIG. 15B.  Needle tip 202 may then be withdrawn proximally
through the tissue, as shown in FIG. 15C, where second anchor 184 also coupled via suture 186 may be ejected from needle lumen 204.  Locking mechanism 188 may then be ejected and drawn over suture 186 until it bears upon second anchor 184 and
approximates first and second anchors 182, 184 towards one another thereby closing tissue opening 172 between the layers of tissue, as shown in FIG. 15D.  Suture 186 may then be detached to leave the anchor assembly 182, 184 and locking mechanism 188 in
place to maintain securement of the closure.  The entire procedure may be performed under direct visualization through the hood 12, if so desired, to ensure sufficient anchor deployment and closure of opening 172.
In yet another variation for effecting closure of a tissue opening, FIG. 16A shows a variation where closure mechanism or patch 210 may be temporarily affixed or releasably coupled about a circumference or lip 218 of hood 12.  A non-porous patch
material 212, which may be fabricated, extruded, woven, etc., from any number of biocompatible materials such as polyester, polypropylene, polyethylene, nylon, PTFE, PFE, polyurethane, etc. or blends thereof, may be supported upon support ring 216, which
may be coupled to hood 12.  Support ring 216 may be fabricated from any number of biocompatible materials such as shape memory alloys, as above, which may enable ring 216 to be configured between a low-profile delivery shape which is positionable within
delivery catheter 16 or a sheath and an expanded shape which conforms to the deployed hood 12.
Support ring 216 may comprise a number of tissue engaging projections 214 which are positioned around ring 216 in a distally projecting orientation such that when expanded and urged against tissue, ring 216 may be secured to the tissue.  As
shown in FIG. 16B, ring 216 may be of a diameter which is sufficiently large enough to encircle the periphery of opening 172 such that patch 212 may completely or at least partially encompass opening 172.  After catheter 16 urges hood 12 and projections
214 into the tissue surrounding opening 172, ring 216 may be detached from hood 12 via a release mechanism to leave ring 216 and patch 212 covering opening 172.  FIG. 16C illustrates an end view of support ring 216 and patch 212 showing one variation
where suture 220 may be routed around the circumference of ring 216 through one or more suture supports 222, e.g., eyelets, openings, etc., to secure ring 216 to hood 12.  When released from hood 12, suture 220 may be pulled proximally to release ring
216 for implantation upon the tissue, thereby allowing hood 12 to be withdrawn from the patient body.
FIG. 17 shows a perspective view of another variation where support ring 230 having patch 212 may have a plurality of barbed projections 232 around a circumference of ring 230 for securing the device to the tissue surrounding the tissue opening. FIGS. 18A and 18B show another variation where support ring 236 may be fabricated from an electrically non-conductive material with a plurality of electrically conductive reconfigurable projections 234 (e.g., electro-active polymer, heat-activatable
shape memory alloys, etc.) inter-connected via a conductive wire 238.  In such a variation, electrical energy provided via power supply 240 through wire 238 may energize projections 234 such that they maintain a straightened configuration during
deployment into the tissue.  Once suitably positioned within the tissue, electrical energy may be switched off 242 such that projections are automatically reconfigured into a curved configuration 234&#39; which inhibits ring 236 from being pulled or
dislodged from the tissue, as shown in FIG. 18B.
In yet another variation utilizing a patch, support ring 216 having patch material 212 may be delivered in a low-profile configuration attached via releasable member 250 through cannula 174, as shown in FIG. 19A.  Once patch 212 is proximate to
the opening to be closed, ring 216 may be deployed or expanded, as shown in FIG. 19B, and placed into position over the opening via cannula 174.  Support ring 216, shown in FIG. 20, may be secured to the underlying tissue via any number of securement
devices which may be passed through the patch 212 and into the tissue for securement.  Some non-limiting examples of securement devices are illustrated in FIGS. 21A to 21D, which shows a variation in FIG. 21A of a multi-barbed securement member which may
be driven via any number of instruments through patch 212 and into the tissue.  FIG. 21B shows another variation of a single-barbed securement member while FIG. 21C shows a securement member configured as a staple 256 and FIG. 21D shows yet another
variation of a securement member configured as a helical screw 258.  FIG. 22 shows an example in the partial cross-sectional view of patch 212 deployed against the atrial septum AS over the tissue opening with a plurality of helical screws 258 driven
through the patch 212 and into the underlying tissue.
FIG. 23 shows a partial cross-sectional view of a heart with another variation of a patch device which utilizes support ring 216, patch material 212 and a securement member 260 which is reconfigurable from a low-profile configuration into an
expanded configuration which inhibits pulling through the tissue.  In this variation, securement member 260 may be fabricated from a shape memory material, as above, which extends from a center of patch 212.  When deployed, member 260 may be passed in a
low-profile configuration through the tissue opening and then released to allow member 260 to reconfigure into its expanded configuration.  Once expanded, it may urge the patch 212 disposed on the opposite side of the tissue opening towards the tissue to
ensure a secure closure of the opening, much like a spring.
FIG. 24A illustrates a perspective view of a variation of the closure device of FIG. 23.  As shown, member 260 may be seen as extending from patch 212 although in this variation, one or more projecting barbs 262 may extend from patch 212 towards
member 260 to additionally secure the patch 212 to the tissue.  FIG. 24B illustrates another variation of patch 212 having the one or more barbs 262 projecting therefrom but without member 260.
Additional variations of patch devices and closure systems are shown and described in further detail in U.S.  patent application Ser.  No. 11/259,498, which has been incorporated by reference above.
Although the devices and methods are described above as utilizing intravascular delivery and deployment, any of the above may be alternatively utilized via a laparoscopic approach.  For instance, as shown in the illustrative view of FIG. 25, any
of the methods and devices may lend themselves to use of a laparoscopic variation 270 utilizing a rigid shaft 272 and handle 274, e.g., for use on an external surface of the heart H, or via an intra-cardiac approach.
The applications of the disclosed invention discussed above are not limited to certain treatments or regions of the body, but may include any number of other treatments and areas of the body.  Modification of the above-described methods and
devices for carrying out the invention, and variations of aspects of the invention that are obvious to those of skill in the arts are intended to be within the scope of this disclosure.  Moreover, various combinations of aspects between examples are also
contemplated and are considered to be within the scope of this disclosure as well.
Tissue closure system, Saadat, Vahid Saadat, Application number 11 560-732, Surgery, closure system, patent search, medical device, Patent Agent, blood vessel, soft tissue, Primary examiner, Assistant examiner, patent data, US patent office
FIELD OF THEINVENTION The present invention relates generally to medical devices used for visualizing and/or closing openings or defects within a body. More particularly, the present invention relates to apparatus and methods for visualizing and/or closing openingsor wounds, e.g., septal defects, patent foramen ovale (PFO), etc., within a patient's body such as within the heart, which are generally difficult to image because of surrounding opaque bodily fluids such as blood.BACKGROUND OF THE INVENTION Conventional devices for visualizing interior regions of a body lumen are known. For example, ultrasound devices have been used to produce images from within a body in vivo. Ultrasound has been used both with and without contrast agents, whichtypically enhance ultrasound-derived images. Other conventional methods have utilized catheters or probes having position sensors deployed within the body lumen, such as the interior of a cardiac chamber. These types of positional sensors are typically used to determine the movement of acardiac tissue surface or the electrical activity within the cardiac tissue. When a sufficient number of points have been sampled by the sensors, a "map" of the cardiac tissue may be generated. Another conventional device utilizes an inflatable balloon which is typically introduced intravascularly in a deflated state and then inflated against the tissue region to be examined. Imaging is typically accomplished by an optical fiber orother apparatus such as electronic chips for viewing the tissue through the membrane(s) of the inflated balloon. Moreover, the balloon must generally be inflated for imaging. Other conventional balloons utilize a cavity or depression formed at a distalend of the inflated balloon. This cavity or depression is pressed against the tissue to be examined and is flushed with a clear fluid to provide a clear pathway through the blood. However, such imaging balloons have many inherent disadvantages. For instance, such b
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