U.S. patent application number 11/457756 was filed with the patent office on 2006-11-02 for electrical block positioning devices and methods of use therefor.
Invention is credited to Richard Cornelius, William Swanson.
Application Number | 20060247607 11/457756 |
Document ID | / |
Family ID | 32965568 |
Filed Date | 2006-11-02 |
United States Patent
Application |
20060247607 |
Kind Code |
A1 |
Cornelius; Richard ; et
al. |
November 2, 2006 |
Electrical Block Positioning Devices And Methods Of Use
therefor
Abstract
The present invention provides positioning mechanisms for
devices that cause conduction blocks or ablation in desired areas
of tissue. The positioning mechanisms allow for variable geometry
of the target sites and enable more accurate therapy at the tissue
site.
Inventors: |
Cornelius; Richard;
(Wayzata, MN) ; Swanson; William; (St. Paul,
MN) |
Correspondence
Address: |
INSKEEP INTELLECTUAL PROPERTY GROUP, INC
2281 W. 190TH STREET
SUITE 200
TORRANCE
CA
90504
US
|
Family ID: |
32965568 |
Appl. No.: |
11/457756 |
Filed: |
July 14, 2006 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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10792111 |
Mar 2, 2004 |
7097643 |
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11457756 |
Jul 14, 2006 |
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60451821 |
Mar 3, 2003 |
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60467298 |
May 1, 2003 |
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Current U.S.
Class: |
606/1 ;
606/41 |
Current CPC
Class: |
A61B 2018/00404
20130101; A61B 90/11 20160201; A61B 2017/00247 20130101; A61M
25/0074 20130101; A61B 18/02 20130101; A61B 18/1477 20130101; A61B
2018/00267 20130101; A61B 2018/144 20130101; A61B 2017/3484
20130101; A61M 25/0082 20130101; C08L 2201/12 20130101; A61B
2018/0016 20130101; A61B 2018/00898 20130101; A61B 2017/3486
20130101; A61M 25/04 20130101; A61B 2018/00279 20130101; A61B 18/18
20130101; A61M 25/0068 20130101; A61N 7/02 20130101; A61B 2018/1475
20130101; A61B 2018/00375 20130101; A61B 2018/00345 20130101; A61B
18/1492 20130101; A61B 2017/00867 20130101; A61B 2018/00392
20130101; A61B 2018/00839 20130101; A61B 2018/1425 20130101; A61M
25/0662 20130101; A61B 90/39 20160201; A61B 2017/22038 20130101;
A61B 2018/00285 20130101; A61B 2018/00214 20130101 |
Class at
Publication: |
606/001 ;
606/041 |
International
Class: |
A61B 17/00 20060101
A61B017/00; A61B 18/14 20060101 A61B018/14 |
Claims
1. A method of creating a conduction block within a body
comprising: providing a treatment device comprising a plurality of
anchoring members, at least some of said plurality of anchoring
members being connected to each other with an associated connective
element; positioning said treatment device adjacent to a target
tissue area within a body; directing said anchoring members into a
tissue of said target tissue area; contacting each connective
element associated with said anchoring members against said target
tissue area; and allowing said anchoring members and each
associated connective element to induce a healing response in said
target tissue area within said body so as to form a conduction
block in said target tissue area.
2. The method of claim 1, wherein the providing of a treatment
device includes providing a treatment device wherein said plurality
of anchoring members and said associated connective element form a
substantially circular treatment device.
3. The method of claim 1, wherein prior to positioning said
treatment device adjacent to a target tissue area said treatment
device is loaded into a delivery device and wherein said
positioning of said treatment device includes expanding a plurality
of arms of said delivery device such that said plurality of arms
place said anchoring members adjacent said target tissue.
4. The method of claim 3, wherein said directing said anchoring
members into a tissue includes urging each of said plurality of
anchoring members into said target tissue with said plurality of
arms of said delivery device.
5. The method of claim 4, wherein said directing said anchoring
members into a tissue of said target tissue area includes piercing
said target tissue with said anchoring members.
6. The method of claim 1, wherein said allowing said anchoring
members and each associated connective element to induce a healing
response in said target tissue includes allowing said anchoring
members and each associated connective element to induce ablation
of said target tissue.
7. The method of claim 1, wherein the target tissue area includes a
path around an ostium of a pulmonary vein.
8. The method of claim 1, wherein said connective element is a
tether.
9. The method of claim 1, wherein said connective element is
comprised of an ablation-causing material.
10. The method of claim 9, wherein said ablation-causing material
is selected from a group consisting of: polyorthoesters,
polycaprolactone, and copper.
11. A method of reducing conduction pathways in heart tissue
comprising: piercing target heart tissue with a plurality of pins
so as to anchor said pins in said target heart tissue; contacting a
tether linking each of said pins together to target heart tissue
between each of said pins; and, allowing said pins and said tether
to induce a healing response on said target heart tissue until a
substantially continuous line of electrical block is formed by said
pins and said tether in said target heart tissue.
12. The method of claim 11, wherein prior to said piercing, said
pins and said tether are delivered to said target heart tissue with
a delivery device.
13. The method of claim 12, wherein said piercing said target heart
tissue with a plurality of pins includes urging arm members of said
delivery device against said plurality of pins so that said
plurality of pins pierce said target heart tissue.
14. The method of claim 11, wherein said piercing said target heart
tissue with said plurality of pins comprises urging said plurality
of pins into heart tissue surrounding an ostium of a pulmonary
vein.
15. The method of claim 11, wherein said contacting a tether to
target heart tissue between each of said pins includes contacting a
tether comprised of an ablative material to said target heart
tissue.
16. The method of claim 11, wherein the forming of a substantially
continuous line of electrical block comprising generating a
continuous line of electrical block around an ostium of a pulmonary
vein.
17. A device for causing ablation within tissue comprising: a
plurality of pins, each of said pins having a first end shaped to
pierce a target tissue; an elongated flexible member coupling each
of said pins together; and, said elongated flexible member
comprised of a material that causes a healing response in
tissue.
18. The device of claim 17, wherein said elongated flexible member
couples said pins together so as to form a generally circular
shape.
19. The device of claim 18, wherein said elongated flexible couples
said pins together so as to form a shape that at least partially
encircles an ostium of a pulmonary vein.
20. The device of claim 17, wherein said plurality of pins and said
elongate flexible member combine to generate a substantially
continuous line of electrical block in said tissue.
Description
CROSS REFERENCE TO RELATED APPLICATIONS
[0001] This application claims the benefit of U.S. Provisional
Application 60/451,821, entitled Positioning Device For Guiding
Device Delivery Or Interventions In Pulmonary Veins Or Other Large
Body Vessels, filed Mar. 3, 2003; and U.S. Provisional Application
60/467,298, entitled Improved Methods And Devices For Creating
Electrical Block At Specific Targeted Sites In Cardiac Tissue,
filed May 1, 2003, the entire contents of each being hereby
incorporated by reference.
BACKGROUND OF THE INVENTION
[0002] Pumping of the human heart is caused by precisely timed
cycles of compartmental contractions of the heart muscle which lead
to an efficient movement of blood into the heart and out to the
various bodily organs and back again to the heart. These precisely
timed cycles are controlled and directed by electrical signals that
are conducted through the cardiac tissue and can be referred to as
pacing signals.
[0003] The sinoatrial node (SA node) is the heart's natural
pacemaker, located in the upper wall of the right atrium. The SA
node spontaneously contracts and generates nerve impulses that
travel throughout the heart wall causing both the left and right
atriums to sequentially contract according to a normal rhythm for
pumping of the heart. These electrical impulses continue to the
atrioventricular node (AV node) and down a group of specialized
fibers called the His-Purkinje system to the ventricles. This
electrical pathway must be exactly followed for proper functioning
of the heart.
[0004] When the normal sequence of electrical impulses changes or
is disrupted, the heart rhythm often becomes abnormal. This
condition is generally referred to as an arrhythmia and can take
the form of such arrhythmias as tachycardias (abnormally fast heart
rate), bradycardias (abnormally slow heart rate) and fibrillations
(irregular heart beats).
[0005] Of these abnormal heart rhythms, fibrillations, and
particularly atrial fibrillations, are gaining more and more
attention by clinicians and health workers. Atrial fibrillation
develops when a disturbance in the electrical signals causes the
two upper atrial chambers of the heart to quiver instead of pump
properly. When this happens, the heart is unable to discharge all
of the blood from the heart's chambers thus creating a situation
where the blood may begin to pool and even clot inside the atrium.
Such clotting can be very serious insofar as the clot can break
away from the atrial chamber and block an artery in the brain, and
thereby cause a stroke in the individual.
[0006] A variety of treatments have been developed over the years
to treat atrial fibrillation, namely, treatments to either mitigate
or eliminate electrical conduction pathways that lead to the
arrhythmia. Those treatments include medication, electrical
stimulation, surgical procedures and ablation techniques. In this
regard, typical pharmacological treatments have been previously
disclosed in U.S. Pat. No. 4,673,563 to Berne et al.; U.S. Pat. No.
4,569,801 to Molloy et al.; and also by Hindricks, et al. in
"Current Management of Arrhythmias" (1991), the contents of which
are herein incorporated by reference.
[0007] Surgical procedures, such as the "maze procedure", have also
been proposed as alternative treatment methods. The "maze"
procedure attempts to relieve atrial arrhythmia by restoring
effective atrial systole and sinus node control through a series of
incisions.
[0008] The maze procedure is an open heart surgical procedure in
which incisions are made in both the left and right atrial walls
which surround the pulmonary vein ostia and which leave a
"maze-like" pathway between the sino-atrial node and the
atrio-ventricular node. The incisions are sewn back together but
result in a scar line which acts as a barrier to electrical
conduction.
[0009] Although the "maze" procedure has its advantages, in
practice it can be a complicated and a particularly risky procedure
to perform since the surgeon is making numerous physical incisions
in the heart tissue. Due in part to the risky nature of the maze
procedure, alternative, catheter-based treatments have been
advanced. Many of these catheter devices create the desired
electrical block by way of ablation devices designed to burn
lesions into the target tissue. Examples of these devices can be
seen in U.S. patents: U.S. Pat. No. 6,254,599 to Lesh; U.S. Pat.
No. 5,617,854 to Munsif; U.S. Pat. No. 4,898,591 to Jang et al.;
U.S. Pat. No. 5,487,385 to Avitall; and U.S. Pat. No. 5,582,609 to
Swanson, all incorporated herein by reference.
[0010] Although ablation catheter procedures remain less invasive
than previous surgical methods like the "maze" procedure, they
nevertheless retain a significant element of risk. For example,
ablation procedures often utilize high power RF energy or
ultrasonic energy, which may adequately create electrical block,
but their inherent destructive nature allows for the possibility of
unintended damage to the target tissue or nearby areas.
[0011] These techniques are used most often in the left or right
atriums by creating electrical block either at discrete sites or
along linear paths. Typically, the sites being targeted are
referenced from landmarks in the chambers of the heart such as the
ostium of the coronary sinus, the pulmonary veins, the tricuspid
valve, the mitral valve, and the inferior and superior vena
cava.
[0012] Currently, commonly used ablation devices are introduced
percutaneously and advanced into the right atrium via the vena cava
and possibly into the left atrium by a transeptal sheath. The
ablation devices are then maneuvered inside the appropriate chamber
of the heart by torquing the shaft of the catheter and deflecting
the tip to bring the ablation tip in contact with the desired
target site.
[0013] Positioning these ablation devices accurately is difficult
as the atrium is a relatively large chamber, having a highly
variable pulmonary vein anatomy which varies from patient to
patient. Additionally, the atrium is constantly moving due to the
beating of the heart and encounters large volumes of blood moving
to and from the pulmonary veins. The blood flow causes difficulty
because typical fluoroscopic techniques of injecting dye into the
blood flow and allowing this to be carried by the blood to fill and
illuminate the desired anatomy require large volume dye injections.
Indeed, in most interventional applications, multiple dye
injections are needed to periodically check the status of the
procedure. This is typically not possible in the pulmonary veins
due to the large volume of dye required for each injection and the
fact that a patient can only tolerate a limited volume of dye
without harming the kidneys.
[0014] One technique currently used to guide ablation catheters
within this difficult environment involves a Lasso.TM. circular
mapping catheter, manufactured by Biosense Webster which is a
Johnson & Johnson company, that places radiopaque mapping
electrodes around the perimeter of the ostium of the pulmonary
veins. The Lasso.TM. circular mapping catheter is so named for its
distal end, heat-set to curl into a ring or lasso shape. A
Lasso.TM. catheter used for this procedure will typically have the
radiopaque electrodes embedded within the lasso segment which
allows the ring to be used as a physical and visual guide for an
ablation catheter. Typically, the Lasso.TM. catheter is positioned
into the atrium until it seats at the ostium of the pulmonary
veins. The radiopaque electrodes act as an atrial ruler for guiding
the ablation catheter to ablate around the ostium.
[0015] The Lasso.TM. catheter, however, is not an optimal solution
for such ablation procedures since the Lasso.TM. catheter may be
easily pushed into the pulmonary vein, causing the doctor to ablate
inside the vein instead of around the ostium. Ablation within the
pulmonary vein increases the risk of pulmonary vein stenosis and is
therefore typically avoided.
[0016] In addition, as previously noted, the geometry of the
pulmonary vein ostium is highly variable, often being more oval
than round. Such variations can cause the Lasso.TM. catheter to be
improperly positioned, further complicating ablation
procedures.
[0017] In view of the above, it is apparent that there is a need
for a positioning system which can more accurately guide
interventions or delivery of devices to the target atrial site
(e.g., the ostium of the pulmonary veins) minimizing the need for
fluoroscopic dye injections.
OBJECTS AND SUMMARY OF THE INVENTION
[0018] It is an object of the present invention to provide an
improved position device that can more accurately guide
interventions or delivery of devices to the ostium of the pulmonary
veins and the atrial walls and thereby provide more accurate
ablation procedures.
[0019] It is a further object of the present invention to provide
an improved catheter that overcomes the drawbacks of the prior
art.
[0020] The present invention achieves the above stated objects by
providing an improved positioning catheter and an improved ablation
catheter which is sized and shaped to better conform to the shape
of the pulmonary veins.
BRIEF DESCRIPTION OF THE DRAWINGS
[0021] FIG. 1 illustrates a side view of a guiding catheter in
according to the present invention;
[0022] FIG. 2 illustrates a side view of the guiding catheter shown
in FIG. 1;
[0023] FIG. 3 illustrates a side view of a guiding delivery
catheter according to the present invention with an implant
delivery catheter tracked over it to the ostium of a pulmonary
vein;
[0024] FIG. 4A illustrates a side view of a balloon guiding
catheter according to the present invention;
[0025] FIG. 4B illustrates a magnified view of the balloon guiding
catheter of FIG. 4A;
[0026] FIG. 5A illustrates a side view of a tension wire guiding
catheter according to the present invention;
[0027] FIG. 5B illustrates a magnified view of the tension wire
guiding catheter of FIG. 5A;
[0028] FIG. 6 illustrates a side view of a guiding catheter with
anchoring pins according to the present invention;
[0029] FIG. 7 illustrates a side view of a friction catheter
according to the present invention;
[0030] FIG. 8 illustrates a side view of a friction catheter with
anchoring balloon according to the present invention;
[0031] FIG. 9A illustrates a side view of an anchoring cage
catheter according to the present invention;
[0032] FIG. 9B illustrates a magnified view of the anchoring cage
catheter of FIG. 9A;
[0033] FIG. 10A illustrates a side view of another anchoring cage
catheter according to the present invention;
[0034] FIG. 10B illustrates a magnified view of the anchoring cage
catheter of FIG. 10A;
[0035] FIG. 11 illustrates a side view of a mesh anchoring ball
catheter according to the present invention;
[0036] FIG. 12 illustrates a side view of the mesh anchoring ball
catheter of FIG. 11;
[0037] FIG. 13 illustrates a view along view lines 13;
[0038] FIG. 14 illustrates a side view of the mesh anchoring ball
catheter of FIG. 11;
[0039] FIG. 15 illustrates a side view of a mesh anchoring ball
catheter according to the present invention;
[0040] FIG. 16 illustrates a side view of a mesh anchoring ball
catheter according to the present invention;
[0041] FIG. 17 illustrates a side view of an opposing arm treatment
catheter according to the present invention;
[0042] FIGS. 18a-18c illustrates a side view of an opposing arm
treatment catheter according to the present invention;
[0043] FIG. 19 illustrates a side view of an opposing arm treatment
catheter according to the present invention;
[0044] FIG. 20 illustrates a side view of an opposing arm treatment
catheter according to the present invention;
[0045] FIG. 21a illustrates a top view of a tethered ablation
device according to the present invention;
[0046] FIG. 21b illustrates a side view of the tethered ablation
device of FIG. 21;
[0047] FIGS. 22a-22c illustrates side views of an expandable linear
ablation device according to the present invention;
[0048] FIG. 23a illustrates a side view of an expandable linear
ablation device according to the present invention;
[0049] FIG. 23b illustrates a side view of an expandable linear
ablation device according to the present invention;
[0050] FIG. 23c illustrates a side view of an expandable linear
ablation device according to the present invention;
[0051] FIGS. 24a-24d illustrate a side view of an expandable linear
ablation device according to the present invention;
[0052] FIG. 25a illustrate a side view of an expandable linear
ablation device according to the present invention;
[0053] FIG. 25b illustrate a side view of an expandable linear
ablation device according to the present invention;
[0054] FIG. 26a illustrate a side view of an expandable linear
ablation device according to the present invention;
[0055] FIG. 26b illustrates a top view of the expandable linear
ablation device of FIG. 26a;
[0056] FIGS. 27a-28e illustrate side views of anchoring pins
according to the present invention;
[0057] FIG. 28 illustrates a side view of a single needle ablation
catheter according to the present invention.
DETAILED DESCRIPTION OF THE INVENTION
Guiding Catheter
[0058] The ostium of the pulmonary veins has a highly variable
geometry from one patient to another and this presents difficulty
in reliably treating atrial arrhythmias using previous ablation
methods. To address this problem, guiding or anchoring devices are
used to position and secure such ablation devices used to create
electrical block.
[0059] One guiding device according to the present invention is a
guiding catheter 102, seen in FIGS. 1-3, which may be positioned
within the pulmonary veins 106. The guiding catheter 102 has a
heat-set distal tip which causes it to self curl into a loop shape
102a, best seen in FIG. 2. Marker rings 108 are spaced along the
distal end of the guiding catheter 102 and are typically composed
of a radiopaque material that allows visibility during a radio
imaging procedure.
[0060] As with some percutaneous transeptal procedures, the guiding
catheter 102 is deployed through the heart septum 112 and into the
left atrium 110 by way of transeptal sheath 114. Such transeptal
procedures often involve advancing the transeptal sheath 114
through the vena cava (not shown) and into the right atrium (not
shown), where it passes through a surgical incision in the septum
112 to the left atrium 110.
[0061] The distal end of the guiding catheter 102 is prevented from
curling in FIG. 1 by a guide wire 104 positioned within the guiding
catheter 102 and controlled at the proximal end of guide device 100
at access hub 116. Once the guiding catheter 102 is positioned
through the ostium 109 and within the pulmonary veins 106, the
guide wire 104 may be retracted into the guiding catheter 102,
allowing the guiding catheter 102 to curl to a loop shape 102a.
Once curled, the guiding catheter 102 will, push against a desired
position, such as the inside of a pulmonary vein 106 or the ostium
109 of a pulmonary vein 106.
[0062] The marker rings 108 of the catheter extend down along the
length of the catheter 102 from the distal ring segment at regular
intervals. These markers act as a ruler to locate positions where
treatment is desired. The lumen for the guide wire 104 can then be
used as a dye injection lumen to get a single image of the
pulmonary veins to clearly show the location and size of the ostium
109. This is an advantage over prior art catheters where the
markers exist only in the segment of the catheter that
self-curls.
[0063] The guiding catheter 102 assists in electrical block
procedures by guiding a second catheter that has a device 122 to
cause ablation of a desired target location as seen in FIG. 3 or by
delivering an electrical block implant device. Many ablation
catheters are known in the art. These catheters often utilize radio
frequency energy, thermal energy, chemical ablation, or mechanical
injury, as seen in the exemplary patents U.S. Pat. Nos. 5,720,775,
4,869,248, 5,405,376, and 5,242,441, all of which are herein
incorporated by reference.
[0064] Implant devices are also used to create electrical block
within a heart and can possibly be delivered using the guiding
catheter 102. Typically, these devices are placed near the ostium
109 of the pulmonary veins 106 or even within the pulmonary veins
106. Exemplary electrical block devices can be seen in commonly
assigned U.S. patent application Ser. No. ______, entitled
Electrical Conduction Block Implant Device, filed ______, the same
filing date as the present application and the contents of which
are herein incorporated by reference.
[0065] Whether an ablation catheter or an electrical block implant
is used for an electrical block procedure, the positioning of the
guiding catheter 102 within the heart is critical for a successful
procedure. Misalignment of the guiding catheter 102 may lead to
ablation of non-target areas within the heart, causing
complications. Similarly, a misaligned guiding catheter 102 may
deliver an implant to the wrong position which may provide poor or
nonexistent electrical block, as well as other complications.
Guiding Catheter With Balloon Segment
[0066] As described above, the guiding catheter 102 seen in FIGS.
1-3, creates a friction fit within an area of the heart due to its
pre-set diameter that is larger than the diameter of the pulmonary
vein 106 or ostium 109. To improve this friction fit, a balloon
segment 204 may be included on the end of balloon guiding catheter
200, as seen in FIGS. 4A and 4B.
[0067] The balloon guiding catheter 200 is an elongated catheter
having a pre-curved distal end and marker rings 202 spaced about
the pre-curved distal end as well as down the catheter away from
the distal end. Like the guiding catheter 102 discussed previously,
the balloon guiding catheter 200 may be positioned transeptally via
a transeptal sheath 114 and can be controlled near access hub
116.
[0068] As shown in FIG. 4B the balloon segment 204 preferably
covers the curved section of the distal tip of balloon guiding
catheter 200, having an internal wire spine 206 which provides the
self curving loop shape. The balloon segment 204 is completely
sealed around the wire spine 206, except for a tube (not shown)
opening within the balloon segment 204 and passing through the
catheter 200 to a media port 208. The media port 208 may be
connected to a device which forces pressurized air or liquid into
the balloon segment catheter 200, expanding the radial size of the
balloon segment 204. The balloon segment 204 may be composed of a
durable, pliable, elastic material that allows the balloon segment
204 to cling tightly to the wire spine 206 when deflated, yet
expand to many times its original diameter when inflated with
media.
[0069] In operation, a user positions the balloon guiding catheter
200 within a left atrium 110 via a transeptal sheath 114. As the
balloon guiding catheter 200 is withdrawn from the transeptal
sheath 114, the balloon segment 204 curls around to a pre-set loop
shape. The balloon segment 204 of balloon guiding catheter 200 is
positioned at a desired target area, typically within the pulmonary
vein 106 or the ostium 109. When the looped balloon segment 204 is
positioned at a desired location, the balloon segment is inflated
with media via the media port 208. As the balloon segment 204
expands, it presses against the pulmonary vein 106 wall or the
ostium 109 wall, providing additional frictional force to anchor
the balloon guiding catheter 200.
Guiding Catheter With Tension Wire
[0070] Referring to FIGS. 5A and 5B, a tension wire guiding
catheter 212 is illustrated which, when deployed within a target
area such as an left atrium, curls around into a loop shape for
anchoring purposes. The tension wire guiding catheter 212 differs
from prior art devices in that it has a tension wire 210 positioned
within a hollow lumen (not shown) of the tension wire guiding
catheter 212. The tension wire 210 passes out of wire aperture 212c
and is fixed to the distal end 212b of the tension wire guiding
catheter 212 while the opposite end of tension wire 210 extends out
of access hub 116.
[0071] As with previously discussed devices, the tension wire
guiding catheter 212 is preferably deployed to a target area such
as the left atrium via the transeptal sheath 114. Within the
sheath, the tension wire guiding catheter 212 remains relatively
straight, with the exposed tension wire 210 in a loose, non-taught
position at the distal tip. Preferably, the distal tip of tension
wire guiding catheter 212 does not have a pre-set curve, however, a
pre-set may be used to assist in creating a desired loop 212a
conformation.
[0072] As the tension wire guiding catheter 212 is withdrawn from
the transeptal sheath 114, the user increases tension on the
tension wire 210 by pulling on the tension wire 210 at the proximal
end, near the access hub 116. As the tension on the tension wire
210 increases, the distal tip of the tension wire guiding catheter
212 bends around into a loop 212a. In this manner, the user can
adjust the diameter of the loop 212a by increasing or decreasing
the tension applied at the proximal end of the tension wire 210.
With such a variable diameter loop 212a, the outward pressure of
the loop 212a against the anchor area (i.e. the pulmonary vein 106
or ostium 109) can be adjusted and thus increased to better secure
the tension wire guiding catheter 212 in place.
Guiding Catheter With Anchoring Pins
[0073] Referring now to FIG. 6, yet another preferred embodiment of
the present invention is illustrated. The anchoring pin guiding
catheter 216 provides additional anchoring support by providing a
plurality of anchoring pins 220 along the distal end of the
anchoring pin guiding catheter 216.
[0074] The overall shape of anchoring pin guiding catheter 216 is
similar to that of previously discussed guiding catheters, in that
it has an elongated shape, sized to fit within the transeptal
sheath 114, marker rings 218 preferably composed of a radiopaque
compound and which extend along the curved distal tip and
downwardly along the catheter, and a pre-set distal tip that
naturally conforms to a loop shape 216a.
[0075] Anchoring pin guiding catheter 216 differs from prior
designs by including multiple anchoring pins 220, preferably
positioned on the distal end of anchoring pin guiding catheter 216,
so as to extend radially outward from the loop 216a. These
anchoring pins 220 may be simple sharp points, barbs, or other
similar designs capable of at least partially penetrating cardiac
or vein tissue. In addition, the anchoring pins 220 are sized so as
to fit within transeptal sheath 114, allowing the anchoring pin
guiding catheter 216 to slide unhindered.
[0076] In operation, a user operates the anchoring pin guiding
catheter 216 in a manner similar to previous designs, beginning by
preferably accessing the left atrium by way of a transeptal
procedure. Once the transeptal sheath 112 is positioned within the
septum 112, the anchoring pin guiding catheter 216 is withdrawn
from the transeptal sheath 114, causing the distal tip of the
catheter 216 to curl around to its natural state, forming a loop
216a with anchoring pins 220 projecting radially away from the
loop's 216a center. The loop 216a is then positioned at a desired
anchoring target, such as within a pulmonary vein 106 or the ostium
109, causing the loop 216 and consequently the anchoring pins 220
to wedge into the anchoring tissue. In this manner, the anchoring
pin guiding catheter 216 maximizes the standard anchoring support
of the typical loop 216a with the anchoring pins 220.
Elongated Friction Catheter
[0077] In another preferred embodiment of the present invention,
best seen in FIG. 7, the anchoring force is achieved by a friction
catheter 221 having a soft, elongated distal end 221a, lacking a
pre-set curve or loop shape. Instead of creating radial force
against the walls of a pulmonary vein as other anchoring catheters
do (e.g. the previous guiding catheter embodiments described in
this application), the present preferred embodiment employs
cumulative friction along the path of the elongated distal end
221a, similar to a coronary guide wire.
[0078] Preferably, the cumulative friction is maximized by
positioning the elongated distal end 221a of the friction catheter
221 to a more distal location within the pulmonary veins 106. The
branches and curves of the pulmonary veins 106 press against
various areas of the elongated distal end 221a, creating friction
along the path of the elongated distal end 221a.
[0079] As with the embodiments described elsewhere in this
application, the friction catheter 221 has marker rings 222 spaced
along its axial length, an access hub 116 for controlling and
manipulating the friction catheter 221, and a transeptal sheath 114
for delivering the friction catheter 221 through the heart septum,
into the left atrium.
[0080] An additional lumen (not shown) may be included within the
friction catheter 221 for providing contrast during a procedure. A
supply of contrast (typically fluoroscopic dye) may be introduced
into the inner contrast lumen via contrast inlet port 223. Under
pressure, the contrast travels through the lumen of the fiction
catheter 221, exiting through exit port 221b. Exit port 221b is
simply an aperture within the friction catheter 221 sidewall, just
distal to the marker rings 222. In this manner, the friction
catheter 221 delivers contrast dye to a desired target area during
a procedure.
[0081] The anchoring force of the friction catheter 221 can be
increased by creating additional friction within the pulmonary vein
106. For example, friction may be created by increasing the length,
flexibility, or material of the elongated distal end 221a.
[0082] Referring to FIG. 8, the anchoring ability of the friction
catheter 224 may be further enhanced with the addition of an
anchoring balloon 228 which can be inflated to press against the
walls of the pulmonary vein 106.
[0083] The balloon friction catheter 224 has an additional media
lumen (not shown), allowing a pressurized media supply such as
saline or contrast to be connected to the media lumen via media
inlet 225. Once within the media lumen, the media moves along the
length of the balloon friction catheter 224 until it reaches
inflation port 230, located at the distal tip, within the balloon
228. The media then fills the balloon 228, which expands to a
desired size to press against the walls of the pulmonary vein
106.
[0084] As with the previously mentioned friction catheter 221, the
balloon friction catheter 224 may include a contrast lumen (not
shown) and a contrast outlet port 224b for providing contrast media
for imaging purposes during the procedure. Additionally, marker
rings 224 may be positioned proximal to the elongated distal end
224a, for further visual reference during a procedure.
Anchoring Cage Catheter
[0085] Referring now to FIGS. 9A, 9B, 10A, and 10B, a preferred
embodiment according to the present invention is illustrated having
an expanding anchoring cage 236 or 240. The anchoring cage catheter
230 creates anchoring force with a cage-like section that can
expand to a greater diameter once positioned in a desired target
location within a pulmonary vein 106.
[0086] FIGS. 9A, 9B show an anchoring cage catheter 230 having an
anchoring cage 236 composed of deformable strips 238. These
deformable strips 238 may be composed of metal, plastic, or other
material that will allow each strip to bend without creasing or
breaking.
[0087] The anchoring cage 236 is located distal to the marker rings
232 to facilitate positioning within the pulmonary vein 106. An
inner control rod 237 is located within anchoring cage catheter
230, and is fixed to distal tip 230a. At the proximal end of the
anchoring cage catheter 230 are catheter handle 234 (fixed to the
anchoring cage catheter 230) and control rod handle 235 (fixed to
the control rod 237), which allow a user to move the control rod
237 relative to the anchoring cage catheter 230.
[0088] Since the control rod 237 is fixed to the distal catheter
end 230, pulling the control rod 237 proximally relative to the
anchoring cage catheter 230 moves the distal catheter tip 230a in a
proximal direction, expanding the deformable strips 238 of the
anchoring cage 236. Thus, a user can expand the anchoring cage 236
to press against the walls of the pulmonary veins 106, providing
anchoring force to maintain a desired position of the anchoring
cage catheter 230.
[0089] FIGS. 10A and 10B illustrate a similar preferred embodiment
of an anchoring cage catheter 230, having an anchoring cage 240
which can be expanded in diameter by the control rod 237. However,
instead of the deformable strips 238 of anchoring cage 236,
anchoring cage 240 is composed of deformable mesh 242. The
deformable mesh 242 can be composed of metal, plastic or any other
material which will allow it to flex without creasing or
breaking.
[0090] By pulling the control rod 237 proximally relative to the
anchoring cage catheter 240 moves the distal catheter tip 230a in a
proximal direction, expanding the deformable mesh 242 of the
anchoring cage 240. Thus, a user can expand the anchoring cage 240
to press against the walls of the pulmonary veins 106, providing
anchoring force to maintain a desired position of the anchoring
cage catheter 240.
Mesh Anchoring Ball Catheter
[0091] Referring now to FIGS. 11-14, a preferred embodiment of a
mesh anchoring catheter 250 is shown according to the present
invention, having an expandable mesh section 252 which can conform
to, and press against the inner wall of a pulmonary vein 106.
[0092] The expandable mesh section 252 is composed of an open mesh
preferably made of metal, plastic, or other flexible material,
which allows blood to flow therethrough. This mesh also conforms to
the shape of the target anchor area, such as an ostium or pulmonary
vein 106. It is common for some ostia to be oval in shape, rather
than circular, yet in these cases the expandable mesh section 252
is capable of conforming to such an oval shape and anchor the mesh
anchoring catheter 250.
[0093] The distal mesh section 252 is initially unexpanded during
transeptal delivery to the left atrium (see FIG. 11). An inner
control shaft 253 within the mesh anchoring catheter 250 controls
the expansion by fixing to the distal end of mesh section 252.
Since the proximal end of the mesh section 252 is fixed to the mesh
anchoring catheter 250 body, a user can pull on the inner control
shaft 253 relative to the mesh anchoring catheter 250, moving the
distal end of mesh section 252 closer to the proximal end, thus
forcing the mesh section 252 outward into a ball shape seen best in
FIGS. 12-14.
[0094] As mentioned earlier, such catheter designs serve as both
anchoring devices and guide mechanisms for treatment catheters and
devices such as ablation catheters. Referring once more to FIGS.
11-14, an ablation catheter 256 having an elongated ablating arm
can be seen which advances over the mesh anchoring catheter 250.
The elongated arm 256a of ablation catheter 256 has a gradual
pre-set curve away from the mesh anchoring catheter 250, due to an
elastic, preconfigured, nitinol core.
[0095] As seen in FIG. 11, the ablation catheter 256 is positioned
within a deployment sheath 255 which prevents the arm of ablation
catheter 256 from curving outward, thus allowing both the
deployment sheath 255 and the ablation catheter 256 to slide within
transeptal sheath 114.
[0096] When the mesh anchoring catheter 250 has been positioned,
with assistance of the distal guide wire 254, and anchored at a
desired location, for example within the pulmonary vein 106, the
deployment sheath 255 is pulled back relative to the ablation
catheter 256 as seen in FIG. 12. With nothing to restrict it, the
ablation arm of ablation catheter 256 moves outward, away from the
mesh anchoring catheter 250 body.
[0097] Referring to FIG. 14, the ablation catheter 256 is advanced
distally, toward the mesh section 252 of mesh anchoring catheter
252. Since the mesh section 252 is in its expanded ball shape, the
arm of ablation catheter 256 is further deflected away from the
mesh anchoring catheter 250, allowing the tip of ablation catheter
256 to contact a desired target area around the ostia 109 of the
pulmonary vein 106.
[0098] The ablation catheter 256 enables the treatment of a focal
site defined by the ball-shaped mesh section 252 seated within the
pulmonary vein 106. Additional target electrical block sites can be
treated with this device by rotating the mechanism to any
additional desired sites around the ball-shaped mesh section 252.
Since the ball-shaped mesh section 252 will conform to a non-round
ostium and the treatment mechanism defines its position off of the
surface of the mesh section 252, these sites can be reached and
treated reliably around the perimeter of the ostium 109, if so
desired. If it is desired to create a full line of electrical block
around the ostium 109, then the device could also have multiple
treatment arms located around the mesh anchoring catheter 250 to
allow multiple points to be treated simultaneously, minimizing the
need to rotate the shaft to create a full line around the ostium
109.
[0099] A handle (not shown) may be provided at the proximal end of
the ablation catheter 256 for facilitating ablation catheter 256
rotation. Additionally, this handle may be indexed to allow greater
rotational control of the rotation of the ablation catheter 256,
and thus the areas where electrical block is created.
[0100] The ablation catheter 256 of this preferred embodiment, as
well as any of the other embodiments of the present invention, may
use a variety of ablation techniques, such as radio frequency,
microwave, cryogenic or similar previously disclosed energy
sources. Further, the tip of the ablation catheter 256 arm may
include a small infusion or needle tip for delivery of a chemical
or drug such as an alcohol which would create an injury to the
target tissue. The ablation catheter 256 arm tip could also include
a delivery mechanism to apply an implant such as a staple to create
the desired the desired electrical block, as described in PCT
Publication No. WO 03/003948, hereby incorporated by reference.
[0101] As seen in FIG. 15, different target areas may be reached by
the ablation catheter with elongated arm 257. The ablation catheter
with elongated arm 257 is similar to the previous embodiment,
having a pre-set curved shape which when unconstrained results in
the tip of the elongated arm 257a contacting the tissue of the
target location spaced radially out from the ball shaped mesh
section 252. However, the elongated arm 257a is longer than the
previously discussed embodiment, allowing the arm 257a to move
outward to a radial diameter of about 4 cm.
[0102] This elongated arm 257a allows a user to ablate target sites
a greater distance in diameter from the mesh anchoring catheter
250, due to its increased length. The outward curve of the
elongated arm 257a can be varied by the deployment sheath 255,
which can be adjusted relative to the ablation catheter 257 to
cover proximal portions of the elongated arm 257a, thus varying the
degree the elongated arm 257a bends outward. In this manner, a user
controls the diameter and rotational position of where the ablation
is to occur. By controlling this radial position of the elongated
ablation arm, it is possible to create linear lesion radially out
from the mesh.
[0103] FIG. 16 illustrates yet another preferred embodiment of the
mesh anchoring catheter 250, having ablation pins 260 positioned
around the circumference of the expanded, ball-shape mesh section
252 for causing electrical block inducing injury to the ostium 109
of the pulmonary vein 106. Ablation pins 260 may be needle shaped,
barbed or any other injury-causing pin shape. Other pin shape
examples may be seen in the commonly owned U.S. provisional patent
application 60/467,298, entitled Improved Methods And Devices For
Creating Electrical Block At Specific Targeted Sites In Cardiac
Tissue, the contents of which are hereby incorporated by
reference.
[0104] In another preferred embodiment (not shown), additional
radiopaque marker bands can be mounted around the perimeter of the
expanded ball-shaped mesh section 252 (described above) to visually
assist a user during a procedure.
[0105] In another preferred embodiment (not shown), the expanded
ball-shaped mesh section 252 (described above) may have
electrocardiogram (EKG) leads located at varying positions around
the circumference of the mesh section 252. These EKG leads maybe
connected through wiring within the mesh anchoring catheter 250,
and out to a monitoring device, allowing a user to further map the
perimeter of the ostium 109 to guide the location of the treatment
mechanism.
[0106] In yet another preferred embodiment (not shown), the
previously described mesh section 252 of mesh anchoring catheter
250 may be replaced with a low pressure balloon having a perfusion
lumen to prevent blood occlusion at the ostium 109. In this manner,
the low pressure balloon expands against the ostium of the
pulmonary vein, allowing the ablation pins or other ablation
devices to create electrical block in a target area.
Catheter with Opposing Treatment Arms
[0107] Referring now to FIG. 17, a preferred embodiment of a
treatment catheter 300 with opposing arms 304 is shown for creating
electrical block. The opposing arms 304 are preconfigured to bend
away from the axis of catheter body 302 and guide wire 308 to an
appropriate diameter which may be defined from a pre-procedure MRI,
or other imaging techniques. At the distal tips of opposing arms
304 are one of any number of ablation devices which may be, for
example, energy, mechanical, chemical, or other known methods.
[0108] The treatment catheter 300 does not require an additional
anchoring/guide catheter since the opposing arms 304 are configured
to contact the target tissue of the pulmonary ostium 109. However,
this treatment catheter 300 may be used with such anchoring/guide
catheters, previous examples of which can be seen in this
application.
[0109] In operation, the treatment catheter 300 operates in much
the same manner as other treatment catheters, in that the treatment
catheter 300 is positioned within the left atrium, possibly
transeptally while the guide wire 308 is directed into the
pulmonary vein 106. Next, the sheath 306 is moved in a proximal
direction to expose the opposing arms 304, which in turn move away
from the axis of the guide wire to a position seen in FIG. 17. The
treatment catheter 300 is then advanced distally towards the
pulmonary vein 106 until the tips of opposing arms 304 contact the
target area of the ostium 109. The treatment arms 304 can be
pressed in contact with the tissue around the ostium 109 at the
desired points for ablation. It can be seen that they can easily be
rotated to ablate additional points. When the procedure is
complete, the sheath 306 may be moved in a distal direction
relative to the catheter body 302, sliding over the opposing arms
304 and compacting the overall size of the treatment catheter 300
for removal from the body.
[0110] While two opposing treatment arms 304 are shown in FIG. 17,
additional treatment arms may be included for treating additional
targets areas at the same time. Additional treatment arms may also
be included as positioning guides to ensure ablation to the proper
target tissue area. It is also anticipated that the treatment arms
304 could be configured with only one treatment arm 304 being a
treatment arm, while one or more additional arms 304 act as
positioning guides.
[0111] Referring to FIG. 20, a similar preferred embodiment is
illustrated, having two opposing treatment arms 334a which branch
from a catheter body 334. A sheath 332 is pulled back by a user
during a procedure to expose the treatment arms 334a that expand
away from the axis of the guide wire 336 and catheter body 334.
Unlike the embodiment of FIG. 17, the treatment arms 334a have a
smaller degree of expansion away from the center axis of the
treatment catheter 330, while also having curved ablation tips at
the ends of the treatment arms 334a. The smaller expansion angle of
the treatment arms 334a allow for position the treatment arms
within the pulmonary vein 106 as opposed to around the ostium 109.
The curved ablation tips of the treatment arms 334a are angled to
contact the walls of the pulmonary vein 106 to cause desired
ablation during a procedure. When finished, the user may simply
slide the sheath 332 distally to cover the treatment arms 334a,
repacking the treatment catheter 330 for removal from the
patient.
[0112] FIGS. 18a-c illustrate another preferred embodiment of a
treatment catheter 310 according to the present invention, having
backwardly angled treatment arms 312a. Generally, the treatment
catheter 310 is similar to the previously described embodiment in
FIG. 17, in that the treatment catheter 310 is positioned into the
left atrium of a patients heart while a guide wire 316 is directed
into the pulmonary vein 106. The treatment catheter 310 differs,
however, from previous embodiments due to backwardly angled
treatment arms 312a. The sheath 314 is fixed to the guide wire 316,
allowing the sheath 314 to move relative to catheter body 312 and
treatment arms 312a. The guide wire 316 is positioned through a
lumen within the treatment catheter body 312, allowing a user at
the proximal end of the catheter 310 to move and manipulate the
guide wire 316 and catheter body 312.
[0113] As seen in FIG. 18a, the treatment catheter 18a is
positioned near the ostium 109 of the pulmonary vein 106. At this
time, the treatment arms 312a are deflected within the sheath 314.
Next, a user moves the guide wire 316 in a distal direction
relative to the catheter body 312, which also moves the sheath 314
away from the catheter body 312, exposing the treatment arms 312a.
Finally, the treatment catheter 310 is moved distally toward the
pulmonary vein 106 until the ablative tips of treatment arms 312a
contact the ostium 109 of the pulmonary vein 106, seen in FIG. 18c.
The catheter body 312 may be rotated during the procedure to
contact multiple points within a target area. As mentioned above,
additional arms 312a may be included for ablating additional target
sites at once or to act as guides to ensure proper treatment
catheter 310 location.
[0114] FIG. 19 illustrates a preferred embodiment similar to that
of FIG. 18a-18c, except for the treatment arms 312a are
preconfigured to expand to a wider angle. This wider expansion
angle allows the treatment arms 312a to expand until they contact
the wall of the pulmonary vein 106, seen at point 320. Thus, a
wider range of pulmonary vein 106 diameters can be treated by
simply increasing preconfigured expansion angle. This also
facilitates treating sites at a known distance around the ostium
109 of the pulmonary vein, defined by the arm 312a length out from
the point which presses against the pulmonary vein wall to the
treatment tip.
[0115] In another preferred embodiment seen in FIGS. 21a and 21b,
multi-arm treatment catheters (not shown), similar to those seen in
the embodiments of FIGS. 17-20, could be used to deploy a series of
pins 342 around the ostium 109 of a pulmonary vein 106, which are
further connected by a tether 344. Each pin 342 may be deployed by
a treatment arm of such a deployment catheter.
[0116] The tether 344 is created from a material which causes an
additional healing response within the target tissue and can
thereby help produce a continuous line of electrical block between
the deployed pins. Possible tether 344 material may include
biodegradeable polymers such as polyorthoesters or
polycaprolactone, engineering polymers such as silicone, or even
metals such as copper. Further examples and details can be seen in
commonly assigned U.S. Provisional Application 60/467,298 entitled
Methods and Devices for Creating Electrical Block at Specific
Targeted Sites in Cardiac Tissue, which is hereby incorporated by
reference.
Expandable Linear Ablation Positioning Devices
[0117] Referring now to FIGS. 22a-22c, a preferred embodiment of an
expandable linear positioning and ablation device 400 is
illustrated, having a conforming electrode 410 positioned by two
retractable electrode arms 408. The conforming electrode 410 is
composed of a linear, flexible material which allows the expandable
positioning and ablation device 400 to conform to irregular tissue
shapes 406 and create a linear ablation pattern.
[0118] FIG. 22a shows the linear positioning and ablation device
400 in a retracted state, with conforming electrode 410 and
retractable electrode arms 408 retracted within constraint sheath
404. As with previous embodiments, the expandable linear
positioning and ablation device 400 is delivered to the left atrium
transeptally, via transeptal sheath 402 through the septum 112.
[0119] FIG. 22b illustrates the linear positioning and ablation
device 400 in a fully extended position, with retractable electrode
arms 408 extended and angled away from the central axis of the
linear positioning and ablation device 400 so as to spread apart
the conforming electrode 410 to a generally linear shape.
[0120] FIG. 22c shows the linear ablation device 400 pressed
against irregular tissue 406, allowing the conforming electrode 410
to conform to the irregular shape of the tissue 406 to create a
linear ablation.
[0121] Although the linear positioning and ablation device 400 may
be used alone, without further guiding devices, the linear
positioning and ablation device 400 may also be used in conjunction
with an anchoring or guiding catheter, examples of which have been
previously disclosed in this application. For example, FIGS. 26a
and 26b illustrate the linear positioning and ablation device 400
in a deployed state with a mesh anchoring catheter 412, similar to
those described in FIGS. 10-16.
[0122] In operation, the linear ablation device 400 is deployed in
a manner described in FIGS. 22a-22c. Next, referring to FIGS. 26A
and 26B, a user rotates the linear positioning and ablation device
400 around the expanded mesh section 414, occasionally pressing the
conforming electrode 410 against the irregular tissue of the ostium
109. In this manner, a linear ablation pattern 418 (seen in FIG.
26B) is formed, creating a continuous pattern of electrical block
around the pulmonary vein 106.
[0123] FIGS. 23a-23c illustrate three different embodiments of the
electrode of the linear positioning and ablation device 400. FIG.
23a shows a magnified view of the previously described conforming
electrode 410, which provides ablation energy, such as radio
frequency (RF), to target ablation tissue.
[0124] FIG. 23b provides a preferred alternative embodiment of the
linear positioning and ablation device 400 having monopolar
ablation electrode needles 420 mounted on a conforming backing 422.
The ablation needles may use a variety of ablation energies, such
as RF, ultrasound, or microwave energy. The conforming backing 422
allows the monopolar ablation needles to conform to irregular
tissue shapes while also providing the benefits of providing the
ablation energy deeper into the tissue, creating a more uniform
ablation through the depth of the tissue.
[0125] FIG. 23c is similar in shape to the previous figure, but
instead utilizes bipolar ablation needles 426 to create an ablation
line on irregular target tissue. To help fit such irregular target
tissue shapes, the bipolar ablation needles 426 are fixed to a
conforming backing 422, providing additional movement and
flexibility between ablation needles 426. As with 23a and 23b, the
present embodiment may use RF, ultrasound, or microwave energy to
create a bipolar ablation line. In this embodiment, the bipolar
ablation needles 426 are configured in two rows. These rows have
opposite polarity during ablation so that only the tissue between
the rows are ablated. Further details may be seen in U.S.
Provisional Application 60/514,428, filed Oct. 24, 2003, entitled
Methods And Devices For Creating Electrical Block At Specific Sites
In Cardiac Tissue With Targeted Tissue Ablation, hereby
incorporated by reference.
[0126] FIGS. 24a-24d illustrate another preferred embodiment of the
linear positioning and ablation device 432 having retractable
anchoring pins 430, 431 for maneuvering the linear positioning and
ablation device into a desired ablating location. The linear
positioning and ablation device 432 is first moved into a desired
initial ablation position using conventional techniques described
above. Next, anchoring needles 430 and 431 are advanced into the
target tissue to hold the position for ablation. After ablating
this location, anchoring needle 430 is retracted, allowing the
linear ablation device 432 to pivot on anchoring needle 431 to a
next desired position of ablation. Anchoring needle 430 will then
be anchored into a new position and the ablation may be performed
on the second target area. In this manner, a continuous line of
ablation is created by "walking" the linear ablation catheter.
[0127] Single removable anchoring needles 442 or 444 may also be
located at the center of conforming electrode 440, as seen in FIGS.
25a and 25b. FIG. 25a shows an elongated anchoring needle 442,
while FIG. 25b shows a smaller anchoring needle 444. Both anchoring
needle designs 442, 444 are presented for maintaining the desired
position of conforming electrode 440, which ensure the ablative
procedure is performed at a desired location.
[0128] Many different designs of anchoring needles may be used for
the preferred embodiments of the linear ablation devices seen in
FIGS. 24a-25b. Indeed, for any ablation devices where it is desired
to provide an anchoring capability, there are many different
concepts for anchoring needles. A few exemplary designs of such
removable anchoring needles can be seen in FIGS. 27a-27e.
[0129] FIG. 27a shows a curved anchoring needle 500 composed of an
elastic material such as nitinol, having a pointed tip 500a. The
anchoring needle 500 is held straight in a delivery sheath 510 due
to the stiffness of the delivery sheath 510 but regains its natural
curved shape as it is advanced out the end of the sheath 510. In
this way it forms a loop through the target tissue 501, providing
anchoring support. The anchoring needle 500 can be reversed by
drawing the needle back into the sheath 510. The anchoring needle
500 for such a system would be preferable to be small enough in
cross section that it would not produce a big enough hole in the
wall of the tissue 501 to cause bleeding if it pierced through the
entire wall thickness.
[0130] FIG. 27b shows another embodiment of an anchoring needle 502
which functions like a rivet. This anchoring needle 502 is also
preferably composed of an elastic material such as nitinol. In this
embodiment, the tip of the anchoring needle 502 is advanced out of
the sheath 510 and pierces the target tissue. A needle segment 502a
immediately behind the sharp tip has a preformed shape which flares
out to a much bigger diameter. This segment expands as it passes
through the tissue of the wall, anchoring the needle 502 in the
tissue 501.
[0131] FIG. 27c shows an anchor needle embodiment which uses a
helical needle which can be screwed into the tissue to anchor and
unscrewed to release.
[0132] FIG. 27d illustrates a barbed needle 506 which functions
like an umbrella. The barb's 506a natural position is tight against
the central shaft. These barbs 506a are splayed out elastically by
a sheath 510 which is advanced forward. The barbs 506a return to
their original position when the sheath 510 is pulled back.
[0133] FIG. 27e illustrates yet another embodiment of a barbed
anchoring needle 508, having barbs 508a formed so their natural
position is in a flared out conformation. The barbs 508a are
constrained by a sheath 509 while piercing the tissue and the
sheath is then advanced to release the barbs 508a. The barbs 508a
have arms 508b which branch off and angle back into the end of
sheath 509. Theses arms 508b act to collapse the barbs 508a when
the sheath is advanced. To withdraw the anchoring needle 508, the
insertion steps are simply reversed.
[0134] FIG. 28 illustrates an ablation catheter 520 with additional
electrodes 524, as is commonly used today, but having a retractable
anchoring needle 522 protruding from its tip. The anchoring needles
serves to better position the ablation catheter 520 in place.
[0135] The retractable anchoring needle 522 may include one of the
previously mentioned needle designs in FIGS. 27A-27E, or other
retractable needle designs. In addition to acting as an anchor, the
retractable anchoring needle 522 may also serve as an ablation
electrode, yielding deeper ablation with less energy. The ablation
catheter 520 may alternatively serve to anchor and guide, while a
user provides a separate ablation catheter, similar to those seen
in FIG. 11-15 where the treatment arm rotates around the perimeter
of the ostium.
[0136] Although the invention has been described in terms of
particular embodiments and applications, one of ordinary skill in
the art, in light of this teaching, can generate additional
embodiments and modifications without departing from the spirit of
or exceeding the scope of the claimed invention. Accordingly, it is
to be understood that the drawings and descriptions herein are
proffered by way of example to facilitate comprehension of the
invention and should not be construed to limit the scope
thereof.
* * * * *