U.S. patent application number 14/060056 was filed with the patent office on 2014-03-13 for transcatheter prosthetic heart valve delivery device with stability tube and method.
This patent application is currently assigned to Medtronic, Inc.. The applicant listed for this patent is Medtronic, Inc.. Invention is credited to Charles Tabor.
Application Number | 20140074227 14/060056 |
Document ID | / |
Family ID | 44202049 |
Filed Date | 2014-03-13 |
United States Patent
Application |
20140074227 |
Kind Code |
A1 |
Tabor; Charles |
March 13, 2014 |
Transcatheter Prosthetic Heart Valve Delivery Device with Stability
Tube and Method
Abstract
A device for percutaneous delivery of a stented prosthetic heart
valve. The device includes a sheath, a handle, and an outer
stability tube. The sheath includes a distal capsule and a proximal
shaft. The handle has a housing maintaining an actuator mechanism
that is coupled to the shaft. The actuator mechanism is configured
to selectively move the shaft, and thus the capsule, relative to
the housing. The stability tube is coupled to the housing and is
coaxially received over the shaft such that the shaft is slidable
relative to the stability tube. In a delivery state, the capsule
encompasses the prosthetic valve. In a deployed state, the capsule
is withdrawn from the prosthetic valve. The shaft slides relative
to the stability tube in transitioning from the loaded state to the
deployed state. When used with an introducer device, the stability
tube frictionally isolates the sheath.
Inventors: |
Tabor; Charles; (St. Louis
Park, MN) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Medtronic, Inc. |
Minneapolis |
MN |
US |
|
|
Assignee: |
Medtronic, Inc.
Minneapolis
MN
|
Family ID: |
44202049 |
Appl. No.: |
14/060056 |
Filed: |
October 22, 2013 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
12759394 |
Apr 13, 2010 |
8579963 |
|
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14060056 |
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Current U.S.
Class: |
623/2.11 |
Current CPC
Class: |
A61F 2250/0039 20130101;
A61F 2/9517 20200501; A61F 2/2436 20130101; A61F 2/2418
20130101 |
Class at
Publication: |
623/2.11 |
International
Class: |
A61F 2/24 20060101
A61F002/24 |
Claims
1. A method for restoring a defective heart valve of a patient, the
method comprising: receiving a delivery device loaded with a
radially expandable prosthetic heart valve having a stent frame to
which a valve structure is attached, the delivery device including
a delivery sheath containing the prosthetic heart valve in a
compressed arrangement and an outer stability tube coaxially
received over the delivery sheath and terminating proximal the
prosthetic heart valve in a delivery state of the delivery device;
establishing an access portal to a bodily lumen of the patient with
an introducer device including an introducer sheath and a valve;
inserting the prosthetic heart valve into the bodily lumen through
the introducer valve while the prosthetic heart valve is
constrained within the delivery sheath, including hemostasis being
established between the introducer valve and the outer stability
tube; manipulating the delivery system to guide the prosthetic
heart valve through the patient's vasculature and into the
defective heart valve; and withdrawing the delivery sheath from the
prosthetic heart valve, including the delivery sheath sliding
relative to the outer stability tube to release the prosthetic
heart valve from the delivery sheath and permitting the prosthetic
heart valve to self-expand into engagement with the native heart
valve.
2. The method of claim 1, wherein withdrawing the delivery sheath
includes the outer stability tube isolating the delivery sheath
from the introducer valve.
3. The method of claim 2, wherein withdrawing the delivery sheath
is characterized by the absence of frictional contact between the
delivery sheath and the introducer device.
4. The method of claim 2, wherein withdrawing the delivery sheath
is characterized by the absence of a sliding force being
transmitted from the delivery sheath onto the introducer device.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a divisional of U.S. application Ser.
No. 12/759,394, filed Apr. 13, 2010, entitled "TRANSCATHETER
PROSTHETIC HEART VALVE DELIVERY DEVICE WITH STABILITY TUBE AND
METHOD", the entire teachings of which are incorporated herein by
reference.
BACKGROUND
[0002] The present disclosure relates to systems and methods for
percutaneous implantation of a prosthetic heart valve. More
particularly, it relates to systems and methods for transcatheter
implantation of a stented prosthetic heart valve.
[0003] Diseased or otherwise deficient heart valves can be repaired
or replaced with an implanted prosthetic heart valve. As used
throughout this specification, the terms "repair," "replace," and
"restore" are used interchangeably, and reference to "restoring" a
defective heart valve is inclusive implanting a prosthetic heart
valve that renders the native leaflets non-functional, or that
leaves the native leaflets intact and functional. Conventionally,
heart valve replacement surgery is an open-heart procedure
conducted under general anesthesia, during which the heart is
stopped and blood flow is controlled by a heart-lung bypass
machine. Traditional open surgery inflects significant patient
trauma and discomfort, and exposes the patient to a number of
potential risks, such as an infection, stroke, renal failure, and
adverse affects associated with the use of the heart-lung machine,
for example.
[0004] Due to the drawbacks of open-heart surgical procedures,
there has been an increased interest in minimally invasive and
percutaneous replacement of cardiac valves. With percutaneous
transcatheter (or transluminal) techniques, a valve prosthesis is
compacted for delivery in a catheter and then advanced, for
example, through an opening in the femoral artery and through the
descending aorta to the heart, where the prosthesis is then
deployed in the annulus of the valve to be repaired (e.g., the
aortic valve annulus). Although transcatheter techniques have
attained widespread acceptance with respect to delivery of
conventional stents to restore vessel patency, only mixed results
have been realized with respect to percutaneous delivery of the
more complex prosthetic heart valve.
[0005] Various types and configurations of prosthetic heart valves
are available for percutaneous valve replacement procedures, and
continue to be refined. The actual shape and configuration of any
particular prosthetic heart valve is dependent to some extent upon
the native shape and size of the valve being replaced or repaired
(i.e., mitral valve, tricuspid valve, aortic valve, or pulmonary
valve). In general, prosthetic heart valve designs attempt to
replicate the function of the valve being replaced and thus will
include valve leaflet-like structures. With a bioprostheses
construction, the replacement valve may include a valved vein
segment that is mounted in some manner within an expandable stent
frame to make a valved stent (or "stented prosthetic heart valve").
For many percutaneous delivery and implantation devices, the stent
frame of the valved stent can be made of a self-expanding material
and construction. With these devices, the valved stent is crimped
down to a desired size and held in that compressed state within an
outer delivery sheath, for example. Retracting the sheath from the
valved stent allows the stent to self-expand to a larger diameter,
such as when the valved stent is in a desired position within a
patient. In other percutaneous implantation systems the valved
stent can be initially provided in an expanded or uncrimped
condition, then crimped or compressed on a balloon portion of a
catheter until it is as close to the diameter of the catheter as
possible. Once delivered to the implantation site, the balloon is
inflated to deploy the prosthesis. With either of these types of
percutaneous stented prosthetic valve delivery devices,
conventional sewing of the prosthetic heart valve to the patient's
native tissue is typically not necessary.
[0006] In addition to the delivery device itself, typical
transcatheter heart valve implantation techniques entail the use of
a separate introducer device to establish a portal to the patient's
vasculature (e.g., femoral artery) and through which the prosthetic
valve-loaded delivery device is inserted. The introducer device
generally includes a relatively short sheath and a valve structure.
By inserting the prosthetic heart valve-loaded sheath through the
introducer valve and sheath, a low friction hemostasis seal is
created around the outer surface of the delivery sheath. While
highly desirable, friction between the introducer device and the
delivery sheath can be problematic, leading to unexpected movement
of the prosthesis prior to release from the delivery device.
[0007] In particular, with a self-expanding stented prosthetic
heart valve, the outer delivery catheter or sheath is retracted
from over the prosthesis, thereby permitting the stented valve to
self-expand and release the prostheses from the delivery device.
Friction between the introducer device and the delivery sheath has
a tendency to resist necessary proximal movement of the delivery
sheath. Because the retraction force is initiated at a handle of
the delivery device, this resistance is transferred to the handle.
As a result, unless the clinician (and/or an assistant) carefully
holds both the handle and the introducer device in a fixed position
relative to one another throughout the deployment operation, the
handle has a tendency to draw forward. This movement, in turn, is
transferred onto the delivery device component (e.g., an internal
shaft) otherwise coupled to the loaded prosthetic heart valve,
potentially moving the internal component (including the loaded
prosthetic heart valve) forward or distally within the patient.
While unintended, even a slight displacement from the expected
deployment location of the prosthesis relative to the native
annulus can lead to severe complications as the prosthesis must
intimately lodge and seal against the native annulus for the
implantation to be successful. If the deployed prosthesis is
incorrectly positioned relative to the native annulus, the deployed
stented valve may leak or even dislodge from the implantation
site.
[0008] For example, FIG. 1A illustrates, in simplified form, an
introducer device 10 establishing a portal to a patient's
vasculature 12, and through which a prosthetic heart valve-loaded
delivery shaft 14 (the tip of which is visible in FIG. 1A) has been
inserted. As shown, the delivery shaft 14 has been manipulated to
locate the loaded prosthetic heart valve 16 (referenced generally)
in a desired position relative to an aortic valve 18. An outer
delivery sheath 20 contains the prosthesis 16. Thus, in the state
of FIG. 1A, the prosthetic heart valve 16 is properly positioned
for deployment from the delivery shaft 14 upon proximal retraction
of the delivery sheath 20 relative thereto, with a spacing S being
established between a distal end of the delivery device's handle 22
and the introducer device 10. As shown in FIG. 1B, an actuator 24
of the handle 22 is moved by the clinician in an attempt to
proximally pull or retract the delivery sheath 20 and release the
prosthesis 16. Frictional interface between the delivery sheath 20
and the introducer device 10 may resist proximal movement of the
delivery sheath 20 (conventionally, the introducer device 10 is
held stationary). As a result, the handle 22 is instead pulled
forward toward the introducer device 10 (reflected in FIG. 1B by a
decrease in the spacing S). In effect, the handle 22 is being
advanced over the delivery sheath 20 rather than the delivery
sheath 20 being retracted into the handle 22. Forward movement of
the handle 22 is, in turn, directed onto the delivery shaft 14,
causing the delivery shaft 14 to distally advance (represented by
the arrow B in FIG. 1B) and displace the deploying prosthetic heart
valve 16 from the desired valve implantation site 18. While it may
be possible to provide an additional isolation layer between the
introducer device 10 and the delivery sheath 20, distinct
constraints render implementation of an additional layer highly
problematic. For example, the tortuous nature of the patient's
vasculature necessitates that the delivery device have as low a
profile as possible, thereby limiting an available size of the
additional layer. Conversely, any additional layers must account
for and facilitate necessary retraction of the delivery sheath 20
during a deployment operation.
[0009] In light of the above, although there have been advances in
percutaneous valve replacement techniques and devices, there is a
continued desired to provide different delivery systems for
delivering cardiac replacement valves, and in particular
self-expanding stented prosthetic heart valves, to an implantation
site in a minimally invasive and percutaneous manner.
SUMMARY
[0010] The delivery devices of the present disclosure can be used
to deliver replacement valves to the heart of a patient. These
replacement heart valves may be configured to provide complementary
features that promote optimal placement of the replacement heart
valve in a native heart valve, such as the aortic valve, mitral
valve, pulmonic valve, and/or tricuspid valve. In some embodiments,
the replacement heart valves of the present disclosure are highly
amenable to transvascular delivery using retrograde transarterial
approach (either with or without rapid pacing). The methodologies
associated with the present disclosure can be repeated multiple
times, such that several prosthetic heart valves of the present
disclosure can be mounted on top of, adjacent to, or within one
another, if necessary or desired.
[0011] The replacement heart valves that are delivered using the
delivery devices and methods of the present disclosure typically
include a stent frame to which a valve structure is attached. These
stent frames can include a wide variety of structures and features
that can be used alone or in combination with features of other
stent frames. In particular, these stent frames provide a number of
different docking and/or anchoring structures that are conducive to
percutaneous delivery thereof. Many of the structures are thus
compressible to a relatively small diameter for percutaneous
delivery to the heart of the patient, and then are expandable via
removal of external compressive forces (i.e., self-expanding
stents). The device is delivered by the delivery devices described
herein can be used to deliver stents, valved stents, or other
interventional devices such as ASD (atrial septal defect) closure
devices, VSD (ventricular septal defect) closure devices, or PFO
(patent foramen ovale) occluders.
[0012] With the above in mind, some aspects in accordance with
principles of the present disclosure relate to a delivery device
for delivering a prosthetic heart valve to a desired location in a
patient. In this regard, the prosthetic heart valve includes a
stent frame to which a valve structure is attached. The delivery
device includes a delivery sheath assembly, a handle, and an outer
stability tube. The delivery sheath assembly defines a lumen, and
includes a distal capsule and a proximal shaft. The capsule is
configured to compressively contain the heart valve prosthesis. The
shaft is coupled to the capsule such that longitudinal movement of
the shaft is transferred to the capsule. The handle includes a
housing and an actuator mechanism. The housing defines a proximal
side and a distal side. The actuator mechanism is maintained by the
housing and is coupled to the shaft, with the shaft extending
distal the distal side of the housing. Further, the actuator
mechanism is configured to selectively move the shaft, and thus the
capsule, relative to the housing. The outer stability tube is
coupled to the housing and is coaxially received over the shaft
such that the shaft is slidable relative to the stability tube.
Finally, a distal end of the stability tube terminates proximal the
capsule in at least a distal-most arrangement of the delivery
sheath assembly. With the above in mind, the actuator mechanism is
operable to transition the delivery device from a loaded or
delivery state to a deployed state. In the loaded state, the
capsule encompasses the prosthetic heart valve. In the deployed
state, the capsule is withdrawn from the prosthetic heart valve. In
this regard, the shaft slides relative to the stability tube in
transitioning from the delivery state to the deployed state. In
some embodiments, the delivery device is used in conjunction with
an introducer device for delivering the prosthetic heart valve into
the patient's vasculature, with the stability tube serving to
isolate the delivery sheath from the introducer device.
[0013] Yet other aspects in accordance with principles of the
present disclosure relate to a system for restoring a heart valve
of a patient, and include a delivery device as described above
along with a prosthetic heart valve. The prosthetic heart valve has
a stent frame and a valve structure attached to the frame and
forming at least two valve leaflets. The prosthetic heart valve is
self-expandable from a compressed arrangement to a natural
arrangement. The system is configured to be transitionable from a
loaded condition in which the prosthetic heart valve is retained
within the capsule of the delivery sheath assembly and a deployed
condition in which the capsule is withdrawn from the prosthetic
heart valve to permit the prosthesis to self-expand to the natural
arrangement and release from the delivery device. In this regard,
the actuator mechanism is configured to effectuate transitioning
from the loaded condition to the deployed condition by sliding the
delivery sheath assembly relative to the prosthetic heart valve and
the outer stability tube.
[0014] Yet other aspects in accordance with principles of the
present disclosure relate to a method for restoring a defective
heart valve of a patient. The method includes receiving a delivery
device loaded with a prosthetic heart valve having a self-expanding
stent frame to which a valve structure is attached. The delivery
device includes a delivery sheath containing the prosthetic heart
valve in a compressed arrangement and an outer stability tube
coaxially received over the delivery sheath and terminating
proximal the prosthetic heart valve. A portal to a bodily lumen of
the patient is established by an introducer device including an
introducer sheath and a valve. The prosthetic heart valve is
inserted into the bodily lumen through the introducer valve while
constrained within the delivery sheath. In this regard, hemostasis
is established between the introducer valve and the outer stability
tube. The delivery device is manipulated to guide the prosthetic
heart valve through the patient's vasculature and into the
defective heart valve. The delivery sheath is withdrawn from over
the prosthetic heart valve, with the delivery sheath sliding
relative to the outer stability tube. The prosthetic heart valve is
released from the delivery device upon withdrawal of the delivery
sheath, and permitted to self-expand into engagement with tissue of
the native heart valve. In some embodiments, the method includes
the outer stability tube isolating the delivery sheath from the
introducer valve such that the delivery sheath does not
frictionally interface with the introducer valve.
BRIEF DESCRIPTION OF THE DRAWINGS
[0015] FIGS. 1A and 1B are simplified illustrations of conventional
transcatheter delivery and implantation of a stented prosthetic
heart valve;
[0016] FIG. 2A is a side view of a stented prosthetic heart valve
useful with systems, devices, and methods of the present disclosure
and in a normal, expanded arrangement;
[0017] FIG. 2B is a side view of the prosthetic heart valve of FIG.
2A in a compressed arrangement;
[0018] FIG. 3 is a perspective view of a percutaneous stented
prosthetic heart valve delivery device in accordance with
principles of the present disclosure;
[0019] FIG. 4 is an exploded perspective view of the delivery
device of FIG. 3;
[0020] FIG. 5A is an enlarged cross-sectional view of a distal
portion of the delivery device in a loaded state;
[0021] FIG. 5B is an enlarged side view of the distal portion of
FIG. 5A in a deployed state;
[0022] FIG. 6 is an exploded perspective view of a handle portion
of the delivery device of FIG. 3;
[0023] FIG. 7 is a cross-sectional view of the delivery device of
FIG. 3;
[0024] FIG. 8A is an enlarged cross-sectional view of a portion of
the delivery device of FIG. 3, illustrating assembly of the handle
to various components;
[0025] FIG. 8B is an enlarged cross-sectional view of a portion of
the delivery device of FIG. 3, illustrating assembly of a distal
region of the handle;
[0026] FIG. 9A is a simplified side view of a system for restoring
(e.g., replacing) a defective heart valve of a patient, including
the prosthetic heart valve of FIG. 2A loaded within the delivery
device of FIG. 3 in a delivery state;
[0027] FIG. 9B is a simplified cross-sectional view of the system
of FIG. 9A;
[0028] FIGS. 10A and 10B illustrate various steps of a method for
replacing or repairing a defective heart valve of a patient in
accordance with principles of the present disclosure;
[0029] FIG. 11A is a simplified side view of a distal portion of
another system, including an alternative delivery device in
accordance with principles of the present disclosure in a delivery
state;
[0030] FIG. 11B is a simplified side view of the system of FIG. 11B
in a partial deployment condition; and
[0031] FIG. 11C is a simplified side view of the system of FIG. 11A
in a re-captured condition.
DETAILED DESCRIPTION
[0032] As referred to herein, the stented prosthetic heart valves
used in accordance with and/or as part of the various systems,
devices, and methods of the present disclosure may include a wide
variety of different configurations, such as a bioprosthetic heart
valve having tissue leaflets or a synthetic heart valve having
polymeric, metallic, or tissue-engineered leaflets, and can be
specifically configured for replacing any heart valve. Thus, the
stented prosthetic heart valve useful with the systems, devices,
and methods of the present disclosure can be generally used for
replacement of a native aortic, mitral, pulmonic, or tricuspid
valve, for use as a venous valve, or to replace a failed
bioprosthesis, such as in the area of an aortic valve or mitral
valve, for example.
[0033] In general terms, the stented prosthetic heart valves of the
present disclosure include a stent maintaining a valve structure
(tissue or synthetic), with the stent having a normal, expanded
arrangement and collapsible to a compressed arrangement for loading
within the delivery device. The stent is normally constructed to
self-deploy or expand when released from the delivery device. For
example, the stented prosthetic heart valve useful with the present
disclosure can be a prosthetic valve sold under the trade name
CoreValve.RTM. available from Medtronic CoreValve, LLC. Other
non-limiting examples of transcatheter heart valve prostheses
useful with systems, devices, and methods of the present disclosure
are described in U.S. Publication Nos. 2006/0265056; 2007/0239266;
and 2007/0239269, the teachings of which are incorporated herein by
reference. The stents or stent frames are support structures that
comprise a number of struts or wire portions arranged relative to
each other to provide a desired compressibility and strength to the
prosthetic heart valve. In general terms, the stents or stent
frames of the present disclosure are generally tubular support
structures having an internal area in which valve structure
leaflets will be secured. The leaflets can be formed from a variety
of materials, such as autologous tissue, xenograph material, or
synthetics as are known in the art. The leaflets may be provided as
a homogenous, biological valve structure, such as porcine, bovine,
or equine valves. Alternatively, the leaflets can be provided
independent of one another (e.g., bovine or equine pericardial
leaflets) and subsequently assembled to the support structure of
the stent frame. In another alternative, the stent frame and
leaflets can be fabricated at the same time, such as may be
accomplished using high-strength nano-manufactured NiTi films
produced at Advanced Bioprosthetic Surfaces (ABPS), for example.
The stent frame support structures are generally configured to
accommodate at least two (typically three) leaflets; however,
replacement prosthetic heart valves of the types described herein
can incorporate more or less than three leaflets.
[0034] Some embodiments of the stent frames can be a series of
wires or wire segments arranged such that they are capable of
self-transitioning from the compressed or collapsed arrangement to
the normal, radially expanded arrangement. In some constructions, a
number of individual wires comprising the stent frame support
structure can be formed of a metal or other material. These wires
are arranged in such a way that the stent frame support structure
allows for folding or compressing or crimping to the compressed
arrangement in which the internal diameter is smaller than the
internal diameter when in the normal, expanded arrangement. In the
compressed arrangement, such a stent frame support structure with
attached valves can be mounted onto a delivery device. The stent
frame support structures are configured so that they can be changed
to their normal, expanded arrangement when desired, such as by the
relative movement of one or more sheaths relative to a length of
the stent frame.
[0035] The wires of the support structure of the stent frames in
embodiments of the present disclosure can be formed from a shape
memory material such as a nickel titanium alloy (e.g., Nitinol).
With this material, the support structure is self-expandable from
the compressed arrangement to the normal, expanded arrangement,
such as by the application of heat, energy, and the like, or by the
removal of external forces (e.g. compressive forces). This stent
frame support structure can also be compressed and re-expanded
multiple times without damaging the structure of the stent frame.
In addition, the stent frame support structure of such an
embodiment may be laser-cut from a single piece of material or may
be assembled from a number of different components. For these types
of stent frame structures, one example of a delivery device that
can be used includes a catheter with a retractable sheath that
covers the stent frame until it is to be deployed, at which point
the sheath can be retracted to allow the stent frame to
self-expand. Further details of such embodiments are discussed
below.
[0036] With the above understanding in mind, one non-limiting
example of a stented prosthetic heart valve 30 useful with systems,
devices and methods of the present disclosure is illustrated in
FIG. 2A. As a point of reference, the prosthetic heart valve 30 is
shown in a normal or expanded arrangement in the view of FIG. 2A;
FIG. 2B illustrates the prosthetic heart valve 30 in a compressed
arrangement (e.g., when compressively retained within an outer
catheter or sheath). The prosthetic heart valve 30 includes a stent
or stent frame 32 and a valve structure 34. The stent frame 32 can
assume any of the forms described above, and is generally
constructed so as to be self-expandable from the compressed
arrangement (FIG. 2B) to the normal, expanded arrangement (FIG.
2A). In other embodiments, the stent frame 32 is expandable to the
expanded arrangement by a separate device (e.g., a balloon
internally located within the stent frame 32). The valve structure
34 is assembled to the stent frame 32 and provides two or more
(typically three) leaflets 36. The valve structure 34 can assume
any of the forms described above, and can be assembled to the stent
frame 32 in various manners, such as by sewing the valve structure
34 to one or more of the wire segments defined by the stent frame
32.
[0037] With the but one acceptable construction of FIGS. 2A and 2B,
the prosthetic heart valve 30 is configured for replacing or
repairing an aortic valve. Alternatively, other shapes are also
envisioned, adapted to the specific anatomy of the valve to be
repaired (e.g., stented prosthetic heart valves in accordance with
the present disclosure can be shaped and/or sized for replacing a
native mitral, pulmonic, or tricuspid valve). With the one
construction of FIGS. 2A and 2B, the valve structure 34 extends
less than the entire length of the stent frame 32, but in other
embodiments can extend along an entirety, or a near entirety, of a
length of the stent frame 32. A wide variety of other constructions
are also acceptable and within the scope of the present disclosure.
For example, the stent frame 32 can have a more cylindrical shape
in the normal, expanded arrangement.
[0038] With the above understanding of the stented prosthetic heart
valve 30 in mind, one embodiment of a delivery device 40 in
accordance with the present disclosure for percutaneously
delivering and implanting the prosthesis 30 is shown in FIG. 3.
Although the delivery device 40 can be loaded with the stented
prosthetic heart valve 30 (FIGS. 2A and 2B) for delivery thereof to
define a system for restoring a defective heart valve, the
prosthesis is not shown in FIG. 3 in order to more clearly
illustrate the components of the delivery device 40. The delivery
device 40 includes a delivery sheath assembly 42, an inner shaft
assembly 44 (referenced generally), an outer tube assembly 46, and
a handle 48. Details on the various components are provided below.
In general terms, however, the delivery device 40 is transitionable
from a loaded or delivery state (shown in FIG. 3) in which the
stented prosthetic heart valve is contained within a capsule 50 of
the delivery sheath assembly 42, to a deployed state in which the
capsule 50 is retracted from the prosthetic heart valve, thereby
permitting the prosthetic heart valve to self-expand (or
alternatively caused to expand by a separate mechanism such as a
balloon) and release from the delivery device 40. As part of this
transitioning, the delivery sheath assembly 42 is slidable relative
to the outer tube assembly 46, and in particular an outer stability
tube 52 component thereof. The delivery device 40 can be used with
a conventional introducer device (not shown), with the outer
stability tube 52 serving to frictionally isolate the delivery
sheath assembly 42 from the introducer device. In other
embodiments, the delivery device 40 is configured to facilitate
user-actuated movement of the stability tube 52 relative to the
delivery sheath assembly 42 and the inner shaft assembly 44, for
example as part of a re-capture procedure described below.
[0039] Components in accordance with some embodiments of the
delivery device 40 are shown in greater detail in FIG. 4. As a
point of reference, various features of the components 42-48
reflected in FIG. 4 and described below can be modified or replaced
with differing structures and/or mechanisms. Thus, the present
disclosure is in no way limited to the delivery sheath assembly 42,
the inner shaft assembly 44, the outer tube assembly 46, the handle
48, etc., shown and described below. In more general terms, then,
delivery devices in accordance with principles of the present
disclosure provide features capable of compressively retaining a
self-expanding, stented prosthetic heart valve (e.g., the capsule
50), along with one or more components (e., the outer stability
tube 52) capable of isolating the delivery sheath assembly 42 from
an introducer device.
[0040] In some embodiments, the delivery sheath assembly 42
includes the capsule 50 and a shaft 60, and defines a lumen 62
(referenced generally) extending from a distal end 64 to a proximal
end 66. In some constructions, the capsule 50 and the shaft 60 are
comprised of differing materials and/or constructions, with the
capsule 50 having a longitudinal length approximating (e.g.,
slightly greater than) a length of the prosthetic heart valve 30
(FIG. 2B) to be used with the device 40. A material and thickness
of the capsule 50 is selected to exhibit sufficient radial rigidity
so as to overtly resist the expected expansive forces of the
prosthetic heart valve 30 when compressed within the capsule 50.
However, the capsule 50 exhibits sufficient longitudinal
flexibility for ready passage through a patient's vasculature and
into a heart valve to be replaced (e.g., retrograde or antegrade
approach). For example, the capsule 50 can include a laser-cut
metal tube that is optionally embedded within a polymer covering.
Alternatively, other constructions are also acceptable, such as a
polymer tube that may or may not be embedded with a metal braiding.
In other embodiments, the capsule 50 is formed of a transparent
material in order to permit a user to see the compressed prosthetic
heart valve when loaded therein (and prior to insertion into the
patient). Optionally, a radiopaque marker 68 can be assembled to
the capsule 50 at or immediately proximal the distal end 64.
[0041] The shaft 60 extends proximally from the capsule 50, and can
be formed as a braided shaft. Other constructions are also
acceptable, with the shaft 60 serving to connect the capsule 50
with the handle 48 as described below. Regardless, the shaft 60 is
coupled to the capsule 50 at a connection point 70 (e.g., heat or
adhesive bonding) to define a discernable proximal end of the
capsule 50, and is constructed to be sufficiently flexible for
passage through a patient's vasculature yet exhibits sufficient
longitudinal rigidity to effectuate desired axial movement of the
capsule 50. In other words, proximal retraction of the shaft 60 is
directly transferred to the capsule 50 and causes a corresponding
proximal retraction of the capsule 50. In some embodiments, the
shaft 60 is configured to transmit a rotational force or movement
onto the capsule 50. In other embodiments, the capsule 50 and the
shaft 60 can be homogeneously formed as a single, continuous tube
or sheath.
[0042] The inner shaft assembly 44 can assume a variety of forms
appropriate for supporting a stented prosthetic heart valve within
the capsule 50. For example, the inner shaft assembly 44 can
include a retention member 80, an intermediate tube 82, and a
proximal tube 84. In general terms, the retention member 80 is akin
to a plunger, and incorporates features for retaining the stented
prosthetic heart valve 30 (FIG. 2B) within the capsule 50 as
described below. The intermediate tube 82 connects the retention
member 80 to the proximal tube 84, with the proximal tube 84, in
turn, coupling the inner shaft assembly 44 with the handle 48. The
components 80-84 can combine to define a continuous lumen 86
(referenced generally) sized to slidably receive an auxiliary
component such as a guide wire (not shown).
[0043] One embodiment of the retention member 80 is shown in
greater detail in FIG. 5A in conjunction with the capsule 50 of a
delivery sheath assembly 42. The retention member 80 can include a
tip 90, a support tube 92, and a proximal hub 94. FIG. 5A further
reflects the lumen 86 as defined along the retention member 80.
[0044] The tip 90 forms or defines a leading nose portion 100 and a
trailing shoulder portion 102. The nose portion 100 defines a
distally tapering outer surface 104 adapted to promote atraumatic
contact with bodily tissue. The shoulder portion 102 is sized to be
slidably received within the distal end 64 of the capsule 50 as
illustrated. The distal end 64 of the capsule 50 and the shoulder
portion 102 are configured to provide a small clearance gap (e.g.,
on the order of 0.001 inch or greater) to permit free movement of
the capsule 50 relative to the tip 90 from the loaded state of FIG.
5A. In some constructions, the shoulder portion 102 can further
define an internally threaded bore 106 for threaded coupling with
the corresponding feature of the support tube 92.
[0045] The support tube 92 is configured to internally support a
compressed, stented prosthetic heart valve generally disposed
thereover, and has a length and outer diameter corresponding with
dimensional attributes of the prosthetic heart valve. While the
support tube 92 is illustrated as being threadably coupled to the
tip 90, other constructions are also acceptable (e.g., the tip 90
and the support tube 92 can be integrally formed as a homogenous
body).
[0046] The hub 94 is attached to the support tube 92 opposite the
tip 90 (e.g., adhesive bond), and provides an engagement feature
110 (referenced generally) configured to selectively capture a
corresponding feature of the prosthetic heart valve. The engagement
feature 110 can assume various forms, and in some constructions
includes a plurality of circumferentially arranged fingers 112 and
a flange 114. The fingers 112 are sized to be received within
corresponding apertures formed by the prosthetic heart valve stent
frame 32 (FIG. 2A). For example, the prosthetic heart valve stent
frame 32 can form wire loops at the proximal end thereof that are
releasably received over respective ones of the fingers 112 and
nest against the hub 94 when compressed within the capsule 50. The
flange 114 is proximally spaced from the fingers 112, with a gap
116 therebetween sized for nested placement of the prosthetic heart
valve's proximal end. With this construction, the capsule 50
captures the stent frame within the gap 116 in the loaded or
delivery state of FIG. 5A. The fingers 112 and the flange 114
impede distal and proximal movement of the prosthetic heart valve
stent frame 32, respectively. In the deployed state of FIG. 5B, the
delivery sheath assembly 42 is retracted relative to the retention
member 80, with the distal end 64 of the capsule 50 being proximal
the flange 114. In this arrangement, then, the prosthetic heart
valve stent frame 32 is no longer constrained within the capsule 50
and thus is free to self-expand (or be caused to expand by a
separate mechanism such as a balloon) and release from the
engagement feature 110. A wide variety of other temporary stent
frame engagement feature configurations are also acceptable. For
example, the hub 94 can form slots sized to slidably receive a
corresponding component of the prosthetic heart valve (e.g., a bar
or leg segment of the stent frame). Further, the inner shaft
assembly 44 can incorporate additional structures and/or mechanisms
that assist in temporarily retaining the prosthetic heart valve
(e.g., a tubular segment biased over the engagement structure 96),
such as described in U.S. Provisional Application Ser. No.
61/237,373 entitled "Transcatheter Valve Delivery Systems and
Methods" filed Aug. 27, 2009 and the entire teachings of which are
incorporated herein by reference.
[0047] Returning to FIG. 4, the intermediate tube 82 is formed of a
flexible material (e.g., PEEK), and is sized to be slidably
received within the delivery sheath assembly 42, and in particular
the shaft 60.
[0048] The proximal tube 84 can include, in some embodiments, a
leading portion 120 and a trailing portion 122. The leading portion
120 serves as a transition between the intermediate and proximal
tubes 82, 84, and thus can be a flexible tubing (e.g., PEEK) having
a diameter slightly less than that of the intermediate tube 82. The
trailing portion 122 has a more rigid construction, configured for
robust assembly with the handle 48. For example, the trailing
portion 122 can be a metal hypotube. In other embodiments, the
intermediate and proximal tubes 82, 84 are integrally formed as a
single, homogenous tube or solid shaft.
[0049] The outer tube assembly 46 can assume various forms and
generally includes the outer stability tube 52. In some
constructions, the outer tube assembly 46 can further include a cap
130 and a flush port construction 132. As described in greater
detail below, the cap 130 rigidly connects the outer stability tube
52 to the handle 48. The flush port construction 132 provides a
pathway for fluidly accessing a space between the outer stability
tube 52 and the delivery sheath assembly 42.
[0050] The outer stability tube 52 serves as a stability shaft for
the delivery device 40, and defines a distal end 140, a proximal
end 142, and a passageway 144 (referenced generally) extending
between, and fluidly open at, the ends 120, 142. The passageway 144
is sized to coaxially receive the delivery sheath assembly 42, and
in particular the shaft 60, in a manner permitting sliding of the
shaft 60 relative to the outer stability tube 52. Stated otherwise,
an inner diameter of the outer stability tube 52 is slightly
greater than an outer diameter of the shaft 60. In some
constructions, a difference between the outer diameter of the shaft
60 and the inner diameter of the outer stability tube 52 is on the
order of 1 French, although other dimensions are also contemplated.
Regardless, and as described in greater detail below, the outer
stability tube 52 has a length selected to extend over a
significant (e.g., at least a majority, in other embodiments
approximately 80%) of a length of the shaft 60 in distal extension
from the handle 48. Further, the outer stability tube 52 exhibits
sufficient radial flexibility to accommodate passage through a
patient's vasculature (e.g., the femoral artery).
[0051] The optional cap 130 is a hub-like body forming a head 150
and a base 152. The head 150 is configured for attachment to the
proximal end 142 of the outer stability tube 52. For example, the
head 150 can form a passageway 154 sized to frictionally receive
the proximal end 142 of the outer stability tube 52. Additional
fixation of the outer stability tube 52 with the head 150 can be
provided (e.g., adhesive, weld, etc.). The base 152 is configured
for rigid attachment to the handle 48 as described below. For
example, in some constructions, the base 152 can form a stepped
ring 156 (referenced generally) configured to connect with a
corresponding feature of the handle 48. The base 152 can further
form a channel 158 sized to slidably receive a component of an
optional purge port construction 160 provided with the handle 48.
Alternatively, the cap 130 can assume a variety of other forms, and
the outer stability tube 52 can be coupled to the handle 48 in a
variety of differing manners that may or may not include the cap
130.
[0052] The optional flush port construction 132, where provided,
includes tubing 170 and a port connector 172. The tubing 170 is
fluidly connected to the passageway 154 of the cap 130 via a radial
hole 174 formed in the head 150. The port connector 172 is fluidly
connected to the tubing 170 and can assume a variety of forms
appropriate for establishing a selective fluid connection to the
tubing 170. For example, in some constructions, the port connector
172 is a luer lock-type structure. In other embodiments, the flush
port construction 132 can be eliminated.
[0053] The handle 48 generally includes a housing 180 and an
actuator mechanism 182 (referenced generally). The handle 48 can
optionally include additional components, such as the purge port
assembly 160. Regardless, the housing 180 maintains the actuator
mechanism 182, with the handle 48 configured to facilitate sliding
movement of the delivery sheath assembly 42 relative to the outer
stability tube 52 and the inner shaft assembly 44 as described
below.
[0054] One optional construction of the housing 180 and the
actuator mechanism 182 is shown in greater detail in FIG. 6. The
housing 180 provides a surface for convenient handling and grasping
by a user, and can have the generally cylindrical shape as shown. A
wide variety of other shapes and sizes are appropriate for user
handling also contemplated. Regardless, the housing 180 forms or
defines a proximal side 190 and a distal side 192. The housing 180
is further configured to maintain portions of the actuator
mechanism 182, for example within an open interior 194 defined by
the housing 180. In some constructions, the housing 180 further
forms a longitudinal slot 196 that is open to the interior 194 and
through which the actuator mechanism 182 extends for interfacing by
a user.
[0055] The actuator mechanism 182 is generally constructed to
provide selective retraction (and optionally advancement) of the
delivery sheath assembly 42 (FIG. 4), and can have a variety of
constructions and/or devices capable of providing the desired user
interface. In the but one acceptable configuration of FIG. 6, the
actuator mechanism 182 includes a sheath connector body 200, a
drive body 202, an actuator assembly 204 (referenced generally),
and a stirrup 206. In general terms, the sheath connector body 200
is configured for assembly to the delivery sheath assembly 42 (FIG.
4), with the actuator assembly 204 selectively locking a
longitudinal position of the sheath connector body 200 relative to
the drive body 202 as part of a sheath movement operation. The
stirrup 206 facilitates insertion and removal of a separate
component (e.g., a guide wire) relative to the delivery device 40
(FIG. 3).
[0056] The sheath connector body 200 has a tubular construction,
defining or forming a leading portion 210, an intermediate portion
216, and a trailing portion 214. The leading portion 210 is
configured for fixed connection with the delivery sheath assembly
42 (FIG. 4), and can form a rim 216 sized to receive a
corresponding component otherwise interconnected to the delivery
sheath assembly 42 as described below. The intermediate portion 212
is sized to slidably nest within the interior 194 of the housing
180, and can optionally form circumferential recesses 218 as shown
to better promote sliding of the sheath connector body 200 relative
to the housing 180 (i.e., the recesses 218 reduce frictional
contact between the sheath connector body 200 and the housing 180).
Further, the intermediate portion 212 is configured for coupling
with a component of the actuator assembly 204 as described below,
and thus can include one or more threaded bores 220.
[0057] The trailing portion 214 is configured for connection to the
actuator assembly 204, as well as to facilitate selective interface
between the actuator assembly 204 and the drive body 202. For
example, in some embodiments, the trailing portion 214 forms a
radial hole 230 and a circumferential slot 232 for reasons made
clear below.
[0058] The drive body 202 has a tubular construction, and forms or
defines a screw region 240, a support region 242, and a control
knob 244. The screw region 240 has an outer diameter sized to be
coaxially received within the sheath connector body 200. Further,
an exterior surface of the screw region 240 forms a helical groove
246.
[0059] The support region 242 extends proximally from the screw
region 240, and has an enlarged diameter. More particularly, the
support region 242 is sized in accordance with an inner diameter of
the housing 180, selected to rotatably support the drive body 202
within the housing interior 194. In some constructions, the support
region 242 can form circumferential recesses 240 as shown for
better promoting rotation of the drive body 202 relative to the
housing 180 where desired (i.e., the surface area of contact
between the support region 242 and the housing 180 is reduced due
to presence of the recesses 248 such that a frictional resistance
to rotation of the drive body 202 is also reduced).
[0060] The control knob 244 extends proximally from the support
region 242, and provides a structured surface 250 adapted to
facilitate user handling. In particular, the control knob 244 is
configured to promote user-directed rotation of the drive body 202
as described below.
[0061] The actuator assembly 204 includes, in some constructions, a
user interface body 260, a locking body 262, and a biasing device
264. The user interface body 260 can assume various shapes and
sizes appropriate for promoting desired handling thereof by a user.
For example, in some constructions, the user interface body 260 is
a cursor-type body providing a contoured external surface 266
shaped to receive a user's thumb. Other shapes differing from those
reflected in FIG. 6 are also acceptable. The interface body 260 can
be viewed as defining a leading section 268 and a trailing section
270, with the leading section 268 being attached to the sheath
connector body 200, and in particular the intermediate portion 212,
for example by one or more couplers (e.g., screws) 272 connected to
the user interface body 260 and secured within the bores 220 of the
sheath connector body 200. Upon final assembly, the user interface
body 260 is longitudinally slidable relative to the housing 180,
and thus can have an interior contour matching an external shape or
curvature of the housing 180.
[0062] The locking body 262 is configured to selectively couple or
lock the sheath connector body 200 relative to the drive body 202.
For example, in some constructions, the locking body 262 is a wire
shaped to define a central segment 274 and opposing arms 276a,
276b. The wire 262 has a diameter slightly less than a width of the
slot 232 in the trailing portion 214 of the sheath connector body
200. Thus, the wire 262 can slidably nest within the slot 232, with
the central segment 274 selectively moving within the slot 232,
into and out of engagement with the helical groove 246 of the drive
body 202 upon final assembly. The arms 276a, 276b are configured
for coupling with the trailing section 270 of the user interface
body 260, and have a length appropriate for engagement and release
of the central segment 274 with the helical groove 246 depending
upon a spatial position of the user interface body 260 as described
below.
[0063] The biasing device 244 includes a spring 280 and a support
pin 282. The spring 280 is assembled between the sheath connector
body 200 and the user interface body 260, and serves to bias the
trailing section 270 of the user interface body 260 away from the
sheath connector body 200. For example, the spring 280 can be
secured within the hole 230 of the sheath connector body 200, with
the support pin 282 maintaining the spring 280 relative to the
bodies 200, 260.
[0064] The optional stirrup 206 includes a guide piece 290 and
opposing legs 292a, 292b. The guide piece 290 forms a port 294
through which an auxiliary component (e.g., a guide wire) can be
inserted and supported. The legs 292a, 292b, project from the guide
piece 290, and are configured for assembly to the proximal side 190
of the housing 180, for example via connectors (e.g., screws)
296.
[0065] Returning to FIG. 4, the optional purge port assembly 160
can include a mounting boss 300, tubing 302, and a port connector
304. The mounting boss 300 is configured to couple the shaft 60 of
the delivery sheath assembly 42 with the sheath connector body 200.
For example, the mounting boss 300 forms a primary lumen 306 having
a diameter approximating an outer diameter of the shaft 60 such
that the proximal end 66 of the shaft 60 can be mounted within the
primary lumen 306. A rear portion 308 of the mounting boss 300 is
configured for coupling with the sheath connector body 200 as
described below, and optionally includes external threads. Finally,
the mounting boss 300 can form a side port 310 sized for attachment
to the tubing 302, with the side port 310 defining a secondary
lumen (not shown) that is fluidly open to the primary lumen
306.
[0066] The tubing 302 can have a flexible construction (e.g.,
Pebax.RTM. material), and is adapted for attachment to the side
port 310 of the mounting boss 300. The port connector 304 is
attached to the tubing 302, and can be configured to provide
selective fluid connection with the tubing 302. For example, in
some constructions, the port connector 304 is a luer lock-type
body.
[0067] Construction of the delivery device 40 is reflected in FIG.
7, and includes the delivery sheath assembly 42 being coaxially and
slidably disposed between the inner shaft assembly 44 and the outer
stability tube 52. As a point of reference, FIG. 7 reflects the
delivery device 40 in the delivery state. As shown, the capsule 50
is coaxially disposed over the retention member 80. Each of the
assemblies 42-46 are connected to the handle 48, with the inner
support assembly 44 and the outer tube assembly 46 being rigidly
coupled to the housing 180. The delivery sheath assembly 42 is
movably connected to the housing 180 via the actuator mechanism 182
as described below. Generally speaking, then, the delivery sheath
assembly 42 can be retracted in a proximal direction relative to
the inner and outer assemblies 44, 46 and the housing 180 from the
loaded or delivery state of FIG. 7 to the deployed state (FIG. 5B).
Regardless, the outer stability tube 52 extends distally from the
distal side 192 of the housing 180, and encompasses at least a
majority of a length of the shaft 50. In some constructions,
however, the outer stability tube 52 terminates proximal the
capsule 50 in at least the delivery state. As shown in FIG. 7, the
distal end 140 of the outer stability tube 52 is proximal the
capsule 50. Further, in some constructions, a length of the outer
stability tube 52 in distal extension from the housing 180 is
selected to be at least slightly proximal the capsule 50 in the
deployed state such that the capsule 50 does not contact the distal
end 140 of the outer stability tube 52, or otherwise enter the
outer stability tube 52, in transitioning from the delivery state
to the deployed state. As a point of reference, the distance of
travel of the delivery sheath assembly 42 in transitioning from the
delivery state to the deployed state is a function of a length of
the selected prosthetic heart valve 30 (FIGS. 2A and 2B). For
example, the distance of travel is slightly greater than a
longitudinal length of the prosthetic heart valve 30 such that in
the deployed state, the capsule 50 is free of the prosthetic heart
valve 30. The distal end 140 of the outer stability tube 52 is thus
located, in the delivery state, proximally along a length of the
shaft 60 at a distance from the capsule 50 (and in particular the
connection 70) commensurate with (e.g., slightly greater than) the
expected length of travel. For example, with constructions in which
the capsule 50, and thus the delivery sheath assembly 42, is
retracted a distance of 8 cm in transitioning from the loaded state
to the deployed state, the distal end 140 of the stability tube 52
is optionally located a distance in the range of 3-13 cm,
optionally approximately 8 cm, proximal of the connection point 70
in the loaded state of FIG. 7. Other dimensional relationships
between the length of extension of the outer stability tube 52
relative to the length of the delivery sheath assembly 42 are also
envisioned. In some embodiments, however, the outer stability tube
52 extends over, and thus stabilizes, as much of the shaft 60 as
possible but does impede sliding/transitioning of the capsule 50
from the delivery state to the deployed state.
[0068] As generally reflected in FIG. 7, the proximal end 142 of
the outer stability tube 52 is rigidly coupled to the housing 180
via the cap 130. For example, as shown in FIG. 8A, the proximal end
142 is affixed within the passage 154 of the head 150. Where
desired, an adhesive can be employed to effectuate a more robust
bond between the outer stability tube 52 and the head 150. The base
152 of the cap 130 is coupled to the distal side 192 of the housing
180. For example, in some constructions, the stepped ring 156 abuts
the distal side 192, and is affixed relative thereto. An adhesive
can further be utilized to bond the cap 130 to the housing 180.
Other mounting constructions are also acceptable and can include,
for example, frictional fit, threaded attachment, etc. FIG. 8A
further reflects the mounting boss 300 disposed within the cap 130,
and coupled to the leading portion 210 of the sheath connector body
200 (e.g., a threaded coupling). The shaft 60 extends within the
cap 130, and is coupled to the mounting boss 300 (e.g., an adhesive
bond). With this construction, the lumen 62 of the delivery sheath
assembly 42 is fluidly open to the primary lumen 306 of the
mounting boss 300. The secondary lumen 312 is also fluidly open to
the primary lumen 306, with FIG. 8A reflecting a fluid connection
being established between the purge tubing 302 and the primary
lumen 306 via the secondary lumen 312. Regardless, a gap 320 is
established between an inner diameter of the outer stability tube
52 and an outer diameter of the shaft 60 as described above. Though
not visible in the view of FIG. 8A, the flush port construction 132
(FIG. 4) is fluidly connected with the gap 320 via the cap 130 as
described above. Optionally, a seal 322 and a retainer 324 can be
provided to fluidly isolate the gap 320.
[0069] The inner shaft assembly 44, and in particular the proximal
tube 84, extends within the lumen 62 of the shaft 60 and through
the mounting boss 300 and the sheath connector body 200. An O-ring
326 can be assembled over the proximal tube 84 as shown, and serves
to fluidly close the primary lumen 306. With this construction,
then, the purge tubing 302 is fluidly open to a spacing 328 between
an interior of the shaft 60 and an exterior of the proximal tube
84, with the O-ring 326 fluidly closing the spacing 328 relative to
the handle 48. Thus, the purge port assembly 160 can be utilized to
effectuate fluid transfer (fluid delivery or vacuum) within an
interior of the capsule 50 (FIG. 7).
[0070] The proximal tube 84 of the inner shaft assembly 44 extends
proximally through the handle 48, including coaxially through the
drive body 202 as shown in FIG. 8B. The proximal tube 84 is
assembled to, and supported by, the stirrup 206. In this regard,
the port 294 of the guide piece 290 is fluidly connected to the
lumen 86 of the proximal tube 84, such that an auxiliary component
(e.g., guide wire) inserted through the port 294 is directly guided
into the inner shaft assembly lumen 86. In some embodiments, the
handle 48 can optionally further include a clamp device 330 (FIG.
4) utilized to secure the proximal tube 84 to the stirrup 206,
although other mounting arrangements are also acceptable.
Regardless, the stirrup 206 is fixed to the housing 180 such that
by mounting the proximal tube 84 to the stirrup 206, the inner
shaft assembly 44 is also fixed relative to the housing 180.
[0071] Returning to FIG. 7, assembly of the handle 48 generally
includes the sheath connector body 200 and the drive body 202 being
disposed within the open interior 194 of the housing 180. The screw
region 240 of the drive body 202 is slidably received within the
sheath connector body 200, with the sheath connector body 200 being
slidable over the screw region 240 (and within the housing 180).
The drive body 202 is located such that the control knob 244 is
proximal the proximal side 190 of the housing 180. With this
construction, the drive body 202 is prevented from sliding relative
to the housing 180, but is allowed to rotate relative thereto. The
actuator assembly 204 selectively links the sheath connector body
200 with the drive body 202. In particular, the user interface body
260 is coupled to the intermediate portion 212 of the sheath
connector body 200 as described above, and is biased to the raised
position of FIG. 7 by the biasing device 264. In this raised
position, the locking body 262 (best shown in FIG. 6) extends
through the slot 232 in the sheath connector body 200, and nests
within the helical groove 246 of the drive body 202. With this
engagement, the locking body 262 prevents longitudinal movement of
the sheath connector body 200 (and thus the delivery sheath
assembly 42) relative to the drive body 202. Conversely, when the
user interface body 260 is pivoted downwardly (relative to the
orientation of FIG. 7), the locking body 262 is moved from
engagement with the drive body 202, thereby permitting sliding
movement of the sheath connector body 200 relative to the drive
body 202. In other words, retraction of the delivery sheath
assembly 42 from the delivery or loaded state to the deployed state
can be accomplished by a user pressing downwardly on the user
interface body 260 to release the locking body 262, and then
retracting (e.g., sliding in the proximal direction) the user
interface body 260 relative to the housing 180. With this
operation, the delivery sheath assembly 42 will retract or slide
relative to the inner shaft assembly 44 and the outer stability
tube 52. When the pressing force is removed, the biasing device 264
operates to move the locking body 262 back into nested engagement
with the helical groove 246 of the drive body 202. Advancement of
the delivery sheath assembly 42 can be achieved in a similar
manner, with the user simply releasing the locking body 262 as
described above, and then moving the user interface body 260
forwardly relative to the housing 180.
[0072] In addition to the coarse movement described above, with the
actuator assembly 204 in the locked state (i.e., the locking body
262 (FIG. 6) engaged with the exterior threads 246 of the drive
body 202), fine tuned movement of the delivery sheath assembly 42
can be achieved by the user rotating the control knob 244. Rotation
of the drive body 202 is transferred onto the locking body 262 via
interface within the helical groove 246. As the locking body 262
rides within the helical groove 246, a force is applied to the user
interface body 260, and thus to the sheath connector body 200. As a
result, rotation of the drive body 202 in a first direction causes
the delivery sheath assembly 42 to slightly retract, whereas
rotation in an opposite direction causes the delivery sheath
assembly 42 to slightly advance. Alternatively, a wide variety of
other constructions can be employed for the actuator mechanism 182
that facilitate user-caused retraction (and optionally advancement)
of the delivery sheath assembly 42.
[0073] During use, the delivery device 40 is initially loaded with
a stented prosthetic heart valve as described above. For example,
FIGS. 9A and 9B illustrate, in simplified form, a distal portion of
a heart valve restoration system 350 in accordance with principles
of the present disclosure, including the stented prosthetic heart
valve 30 loaded within the delivery device 40. As a point of
reference, the system 350 is in a delivery condition in FIGS. 9A
and 9B, with the delivery device 40 arranged in the delivery or
loaded state. The prosthetic heart valve 30 is crimped over the
inner shaft assembly 44 to engage the engagement structure 110. The
capsule 50 compressively contains the prosthesis 30 in the
compressed arrangement. Finally, the stability tube 52 is coaxially
arranged over the shaft 60 of the delivery sheath assembly 42, with
the distal end 140 located proximal the proximal end 70 of the
capsule 50. The delivery device 40 is then manipulated to deliver
the compressed prosthetic heart valve 30 to the heart valve to be
repaired. Once positioned, the capsule 50 is retracted via
operation of the actuator mechanism 182 (FIG. 6), thereby
permitting the prosthetic heart valve 30 to self-expand and deploy.
In some embodiments, prior to full deployment the prosthetic heart
valve 30, the capsule 50 can be advanced back over the prosthetic
heart valve 30 for permitting movement to a new location. The
delivery devices shown and described herein can be modified for
delivery of balloon-expandable stented heart valves, within the
scope of the present disclosure. That is to say, delivery of
balloon-expandable stented heart valves can be performed
percutaneously using modified versions of the delivery devices of
the present disclosure. In general terms, this includes providing
the transcatheter delivery assembly akin to those described above,
along with a balloon catheter and a guide wire.
[0074] In some embodiments, the delivery device 40 can be used in
conjunction with an introducer device 400 as shown in FIG. 10A.
Introducer devices 400 are known in the art, and generally include
an introducer sheath 402 and a valve 404. The introducer sheath 402
is typically a resilient body. To access a bodily lumen (e.g.,
femoral artery) of the patient, an incision 406 is formed in the
patient's skin, and the introducer sheath 402 inserted through the
incision and into the desired bodily lumen. The valve 404 fluidly
closes the connection with the bodily lumen external the patient.
The delivery device 40 is then inserted into the bodily lumen via
the introducer device 400. As generally reflected in FIG. 10A, for
example, the introducer sheath 402 has an inner diameter greater
than that of the outer stability tube 52 (as well as the capsule
50), such that the capsule 50 can readily be delivered through the
bodily lumen, directed to other branches of the patient's
vasculature, and then to the defective heart valve implantation
site 410 (e.g., aortic heart valve). In this regard, the introducer
valve 404 frictionally contacts the outer stability tube 52,
thereby establishing a low friction hemostasis seal around the
outer stability tube 52. Notably, however, the outer stability tube
52 isolates the delivery sheath assembly 42 (and in particular the
shaft 60) from the introducer sheath 402 and valve 404. Stated
otherwise, while the outer stability tube 52 is in physical contact
with portions of the introducer device 400, the delivery sheath
assembly 42 does not directly contact the introducer device 400.
Further, the stability tube 52 overtly supports the delivery shaft
60 in traversing the tortuous vasculature, minimizing occurrences
of kinks forming in the shaft 60 when, for example, moving across
the aortic arch 412.
[0075] With reference to FIG. 10B, to deploy the prosthetic heart
valve 30 (drawn schematically in FIG. 10B) from the delivery device
40, the handle 48 is operated to distally retract the delivery
sheath assembly 42. In particular, the capsule 50 (hidden in FIG.
10B) is withdrawn from over the prosthetic heart valve 30, thereby
permitting the prosthetic heart valve 30 to self-deploy from the
delivery device 40. In this regard, due to the presence of the
stability tube 52, with transitioning of the delivery device 40
from the delivery state to the deployment state via sliding of the
delivery sheath assembly 42, the delivery sheath assembly 42 does
not bear against or otherwise frictionally interface with the
introducer device 400. As a result, unlike previous percutaneous
delivery procedures, the clinician and/or an assistant are not
required to carefully monitor spacing between a handle 48 and the
introducer device 400 while constantly correcting for any
discrepancies as no frictional interface is established during
retraction of the delivery sheath assembly 42. Further, because the
distal end 140 of the stability tube 52 is in close proximity to
the capsule 50, an overall stabilization of the delivery sheath 42
during retraction thereof is provided.
[0076] While the delivery device 40 has been described as spatially
affixing the stability tube 52 relative to the inner shaft assembly
44 (FIG. 3) via the handle 48 (i.e., the delivery sheath assembly
42 is movable relative to the stability tube 52, but not
vice-versa), other constructions are also envisioned. For example,
the handle 48 can be configured to provide a second actuator
mechanism that permits a user to longitudinally move the stability
tube 52 relative to the delivery sheath assembly 42 and the inner
shaft assembly 44, for example to effectuate re-capture or
re-sheathing of a partially deployed prosthetic heart valve. For
example, FIG. 11A illustrates a distal portion of an alternative
delivery device 500 that includes a delivery sheath assembly 502,
an inner shaft assembly 504 (referenced generally), and a stability
tube 506. Though not shown, the components 502-506 are proximally
maintained by a handle. The handle is akin to the handle to the
handle 48 (FIG. 3) described above, and provides at least two
actuator mechanisms; a first actuator mechanism configured to
effectuate user-caused movement of the delivery sheath assembly 502
relative to the inner shaft assembly 504 and the stability tube
506, and a second actuator mechanism configured to effectuate
user-caused longitudinal movement of the stability tube 506
relative to the delivery sheath assembly 502 and the inner shaft
assembly 504.
[0077] The delivery sheath assembly 502 can incorporate any of the
constructions described above, and can be akin to the delivery
sheath assembly 42 (FIG. 3). Thus, for example, the delivery sheath
assembly 502 can include a distal capsule 508 and a proximal shaft
510. As with previous embodiments, the capsule 508 is configured to
compressively contain a stented percutaneous heart valve (not
shown), with the shaft 510 connecting the capsule 508 to the handle
(not shown). The inner shaft assembly 504 can similarly assume any
of the constructions described above, and thus can be akin to the
inner shaft assembly 44 (FIG. 3). In more general terms, then, the
inner shaft assembly 504 incorporates or includes one or more
engagement features (not shown) configured to releasably engage the
stented prosthetic heart valve otherwise disposed within the
capsule 508.
[0078] The stability tube 506 is akin to the stability tube 52
(FIG. 3) described above, and includes a tubular body 520 and one
or more support elements 522 (referenced generally). The tubular
body 520 can be a surgically safe, circumferentially flexible
sheath (e.g., a polymer catheter) sized to be slidably received
over the delivery sheath shaft 510. The tubular body 520 terminates
at distal end 524. In some constructions, a longitudinal cut (not
shown) can be formed along the tubular body 520 to permit
circumferential expansion as described below. Alternatively, the
tubular body 520 can be uniform. The support members 522
circumferentially reinforce the tubular body 520 in a manner
permitting elastic radial expansion. For example, the reinforcement
members 522 can be a series of coil springs. The reinforcement
members 522 can be formed over the tubular body 520, or can be
embedded within a thickness thereof. In other embodiments, the
reinforcement members 522 can be embedded Nitinol zigs, coils, or
other elastic elements.
[0079] In the delivery state of FIG. 11A, the capsule 508
compressively retains the stented prosthetic heart valve (hidden in
the view of FIG. 11A) in a compressed arrangement over the inner
shaft assembly 504. The distal end 524 of the stability tube 506 is
located proximal the capsule 508. The delivery device 500 can then
be manipulated as described above to percutaneously deliver the
stented prosthetic heart valve, in the compressed arrangement, to
the heart valve to be restored.
[0080] The delivery sheath assembly 502 can then be retracted as
described above to release the stented prosthetic heart valve
(hidden in the view of FIG. 11A) from the confines of the capsule
508. In some embodiments, the clinician may desire to only
partially release the stented prosthetic heart valve from the
delivery device 500 and then evaluate a position relative to the
implantation site. For example, FIG. 11B illustrates the delivery
device 500 in a partially deployed state, with the capsule 508
being partially retracted from the stented prosthetic heart valve
30. As shown, a distal region 530 of the prosthesis 30 is exposed
relative to the capsule 508, and has self-expanded toward the
natural, expanded arrangement. A proximal region (hidden in FIG.
11B) remains within the capsule 508 and coupled to the inner shaft
assembly 504. In the partially-deployed state of FIG. 11B, then,
the clinician can evaluate a position of the stented prosthetic
heart valve 30 prior to full release or deployment from the
delivery device 500.
[0081] Under circumstances where the clinician determines that the
prosthetic heart valve 30 should be repositioned, a re-capturing
procedure is performed. In particular, the stability tube 506 is
distally advanced over the capsule 508 and the distal region 530 of
the stented prosthetic heart valve 30. As shown, the reinforcement
members 522 provide necessary circumferential support to the
tubular member 520, thereby facilitating recapturing (and
re-compressing) of the distal region 530.
[0082] FIG. 11C illustrates the delivery device 500 in a
re-captured state, with the stability tube 506 disposed over, and
thus compressing, the previously-deployed distal region 530 (FIG.
11B) of the stented prosthetic heart valve 30 (FIG. 11B). In other
words, the distal end 524 of the stability tube 506 is now distal
the prosthetic heart valve 30. Under circumstances where the
reinforcement members 522 are sufficient to cause the diameter of
the distal end 524 to return approximately to the initial diameter
of the capsule 508 (FIG. 11A), the delivery sheath assembly 502
(FIG. 11A) can be driven retrograde back through the stenotic
valve. Conversely, if the distal end 524 of the stability tube 506
does not return to the initial diameter of the capsule 508, the
delivery sheath assembly 502 (FIG. 11A) can be driven distally to
completely re-sheath the stented prosthetic heart valve 30. Once
the prosthetic heart valve 30 (in the compressed arrangement) has
been desirably repositioned, full deployment can be effectuated as
described above.
[0083] The stented prosthetic heart valve delivery devices and
methods of the present disclosure provide a marked improvement over
previous designs. By isolating the delivery sheath from the
introducer device, potential complications associated with previous
configurations are overcome.
[0084] Although the present disclosure has been described with
reference to preferred embodiments, workers skilled in the art will
recognize that changes can be made in form and detail without
departing from the spirit and scope of the present disclosure.
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