U.S. patent application number 15/404492 was filed with the patent office on 2017-05-11 for devices for therapeutic vascular procedures.
This patent application is currently assigned to SEQUENT MEDICAL, INC.. The applicant listed for this patent is SEQUENT MEDICAL, INC.. Invention is credited to TODD HEWITT, Brian E. Merritt, William R. Patterson, Claudio Plaza, James M. Thompson, Hung P. Tran.
Application Number | 20170128077 15/404492 |
Document ID | / |
Family ID | 56798559 |
Filed Date | 2017-05-11 |
United States Patent
Application |
20170128077 |
Kind Code |
A1 |
HEWITT; TODD ; et
al. |
May 11, 2017 |
DEVICES FOR THERAPEUTIC VASCULAR PROCEDURES
Abstract
Methods and devices for removing a thrombus are described. The
device includes an expandable cylindrical structure made of wires
and a self-expanding permeable shell located at the distal end of
the cylindrical structure. Methods and devices for treating a
cerebral aneurysm are described. The device may include a
self-expanding resilient permeable shell and a metallic coil
secured to the distal end of the permeable shell.
Inventors: |
HEWITT; TODD; (Laguna
Niguel, CA) ; Merritt; Brian E.; (San Clemente,
CA) ; Patterson; William R.; (Huntington Beach,
CA) ; Thompson; James M.; (Lake Forest, CA) ;
Plaza; Claudio; (Rancho Santa Margarita, CA) ; Tran;
Hung P.; (Westminster, CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
SEQUENT MEDICAL, INC. |
ALISO VIEJO |
CA |
US |
|
|
Assignee: |
SEQUENT MEDICAL, INC.
ALISO VIEJO
CA
|
Family ID: |
56798559 |
Appl. No.: |
15/404492 |
Filed: |
January 12, 2017 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
14684212 |
Apr 10, 2015 |
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15404492 |
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62093313 |
Dec 17, 2014 |
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61979416 |
Apr 14, 2014 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61B 17/12145 20130101;
A61B 17/12177 20130101; A61B 17/12172 20130101; A61B 2017/00893
20130101; A61B 2017/00898 20130101; A61F 2310/00149 20130101; A61M
2025/0042 20130101; A61B 2017/12068 20130101; A61B 17/1214
20130101; A61B 17/1215 20130101; A61B 17/12031 20130101; A61B
2017/00526 20130101; A61B 2017/1205 20130101; A61B 2090/3966
20160201; A61B 17/12113 20130101; A61B 2017/00867 20130101 |
International
Class: |
A61B 17/12 20060101
A61B017/12 |
Claims
1. A device for treatment of an aneurysm within a patient's
vasculature, comprising: a self-expanding resilient permeable shell
having a proximal end, a distal end, and a longitudinal axis, the
shell comprising a plurality of elongate resilient filaments having
a braided structure, wherein the plurality of filaments are secured
at least at one of the proximal end or the distal end thereof; a
metallic coil formed from a wire having a first diameter, wherein
the metallic coil is secured at the distal end of the
self-expanding resilient permeable shell; wherein the permeable
shell has a radially constrained elongated state configured for
delivery within a microcatheter and has an expanded state with a
globular, axially shortened configuration relative to the radially
constrained state, the permeable shell having a plurality of
openings formed between the braided filaments; and wherein the
metallic coil has a linear, straightened shape configured for
delivery within a microcatheter.
2. The device of claim 1, wherein the metallic coil is configured
to place a bias on the permeable shell when the permeable shell is
in the expanded state within an aneurysm.
3. The device of claim 1, wherein the metallic coil when at least
partially compressed in an axial direction applies an axial bias of
at least 0.27 grams
4. The device of claim 1, wherein the metallic coil when at least
partially compressed in an axial direction applies an axial bias of
at least 2.67 grams.
5. The device of claim 1, wherein the metallic coil when at least
partially compressed in an axial direction applies an axial bias,
of at least 16.6 grams.
6. The device of claim 1, wherein the metallic coil is configured
to conform to a three-dimensional framing shape.
7. The device of claim 1, wherein the metallic coil is formed from
wire comprising platinum.
8. The device of claim 1, wherein the metallic coil has an expanded
state having at least one loop having a secondary diameter.
9. A method for treating a cerebral aneurysm, comprising the steps
of: providing an implant structure comprising; a sell expanding
resilient permeable shell having a proximal end, a distal end, and
a longitudinal axis, the shell comprising a plurality of elongate
resilient filaments having a braided structure, wherein the
plurality of filaments are secured at least at one of the proximal
end or the distal end thereof; a metallic coil formed from a wire
having a first diameter, wherein the metallic coil is secured at
the distal end of the self-expanding resilient permeable shell;
wherein the permeable shell has a radially constrained elongated
state configured for delivery within a microcatheter and has an
expanded state with a globular, axially shortened configuration
relative to the radially constrained state, the permeable shell
having a plurality of openings formed between the braided
filaments; and wherein the metallic coil has a linear, straightened
shape configured for delivery within a microcatheter; advancing the
implant within a microcatheter to a region near the cerebral
aneurysm; deploying the implant within the cerebral aneurysm, the
metallic coil positioned near a dome of the cerebral aneurysm and
assuming the expanded state and the permeable shell assuming the
expanded deployed state within the cerebral aneurysm; and
withdrawing the microcatheter from the region near the cerebral
aneurysm after deploying the implant.
10. The method of claim 9, wherein the metallic coil pushes the
permeable shell against an opening of the cerebral aneurysm.
11. The method of claim 9, wherein the metallic coil tracks around
a diameter of the cerebral aneurysm.
12. The method of claim 9, wherein the secondary diameter of the
metallic coil is approximately equal to a diameter of the permeable
shell.
13. The method of claim 9, wherein the metallic coil, when at least
partially compressed in an axial direction, applies an axial bias
of at least 0.27 grams.
14. The method of claim 9, wherein the metallic coil, when at least
partially compressed in an axial direction applies an axial bias of
at least 2.67 grams.
15. The method of claim 9, wherein the metallic coil, when at least
partially compressed in an axial direction, applies an axial bias
of at least 16.6 grams.
16. The method of claim 9, wherein the metallic coil has an
expanded state having at least one loop having a secondary
diameter.
Description
RELATED APPLICATIONS
[0001] This application is a continuation of U.S. application Ser.
No. 14,684,212, filed Apr. 10, 2015, which claims priority to U.S.
Provisional Application Ser. No. 61/979,416, filed Apr. 14, 2014,
and U.S. Provisional Application Ser. No. 62/093,313, filed Dec.
17, 2014, all of which are herein incorporated by reference in
their entirety for all purposes.
FIELD OF THE INVENTION
[0002] Embodiments of devices and methods herein are directed to
blocking a flow of fluid through a tubular vessel or into a small
interior chamber of a saccular cavity or vascular defect within a
mammalian body. More specifically, embodiments herein are directed
to devices and methods for treatment of a vascular defect of a
patient including some embodiments directed specifically to the
treatment of cerebral aneurysms of patients.
BACKGROUND
[0003] The mammalian circulatory system is comprised of a heart,
which acts as a pump, and a system of blood vessels that transport
the blood to various points in the body. Due to the force exerted
by the flowing blood on the blood vessel the blood vessels may
develop a variety of vascular defects. One common vascular defect
known as an aneurysm results from the abnormal widening of the
blood vessel. Typically, vascular aneurysms are formed as a result
of the weakening of the wall of a blood vessel and subsequent
ballooning and expansion of the vessel wall. If, for example, an
aneurysm is present within an artery of the brain, and the aneurysm
should burst with resulting cranial hemorrhaging, death could
occur.
[0004] Surgical techniques for the treatment of cerebral aneurysms
typically involve a craniotomy requiring creation of an opening in
the skull of the patient through which the surgeon can insert
instruments to operate directly on the patient's brain. For some
surgical approaches, the brain must be retracted to expose the
parent blood vessel from which the aneurysm arises. Once access to
the aneurysm is gained, the surgeon places a clip across the neck
of the aneurysm thereby preventing arterial blood from entering the
aneurysm. Upon correct placement of the clip the aneurysm will be
obliterated in a matter of minutes. Surgical techniques may be
effective treatment for many aneurysms. Unfortunately, surgical
techniques for treating these types of conditions include major
invasive surgical procedures that often require extended periods of
time under anesthesia involving high risk to the patient. Such
procedures thus require that the patient be in generally good
physical condition in order to be a candidate for such
procedures.
[0005] Various alternative and less invasive procedures have been
used to treat cerebral aneurysms without resorting, to major
surgery. Some such procedures involve the delivery of embolic or
filling materials into an aneurysm. The delivery of such
vaso-occlusion devices or materials may be used to promote
hemostasis or fill an aneurysm cavity entirely. Vaso-occlusion
devices may be placed within the vasculature of the human body,
typically via a catheter, either to block the flow of blood through
a vessel with an aneurysm through the formation of an embolus or to
form such an embolus within an aneurysm stemming from the vessel. A
variety of implantable, coil-type vaso-occlusion devices are known.
The coils of such devices may themselves be formed into a secondary
coil shape, or any of a variety of more complex secondary shapes.
Vaso-occlusive coils are commonly used to treat cerebral aneurysms
but suffer from several limitations including poor packing density,
compaction due to hydrodynamic pressure from blood flow, poor
stability in wide-necked aneurysms and complexity and difficulty in
the deployment thereof as most aneurysm treatments with this
approach require the deployment of multiple coils.
[0006] Another approach to treating aneurysms without the need for
invasive surgery involves the placement of sleeves or stents into
the vessel and across the region where the aneurysm occurs. Such
devices maintain blood flow through the vessel while reducing blood
pressure applied to the interior of the aneurysm. Certain types of
stents are expanded to the proper size by inflating a balloon
catheter, referred to as balloon expandable stents, while other
stents are designed to elastically expand in a self-expanding
manner. Some stents are covered typically with a sleeve of
polymeric material called a graft to form a stent-graft. Stems and
stent-grafts are generally delivered to a preselected position
adjacent a vascular defect through a delivery catheter. In the
treatment of cerebral aneurysms, covered stems or stent-grafts have
seen very limited use due to the likelihood of inadvertent
occlusion of small perforator vessels that may be near the vascular
defect being treated.
[0007] In addition, current uncovered stems are generally not
sufficient as a stand-alone treatment. In order for stents to fit
through the microcatheters used in small cerebral blood vessels,
their density is usually reduced such that when expanded there is
only a small amount of stent structure bridging the aneurysm neck.
Thus, they do not block enough flow to cause clotting of the blood
in the aneurysm and are thus generally used in combination with
vaso-occlusive devices, such as the coils discussed above, to
achieve aneurysm occlusion.
[0008] A number of aneurysm neck bridging devices with defect
spanning portions or regions have been attempted; however, none of
these devices has had a significant measure of clinical success or
usage. A major limitation in their adoption and clinical usefulness
is the inability to position the defect spanning portion to assure
coverage of the neck. Existing stent delivery systems that are
neurovascular compatible (i.e., deliverable through a microcatheter
and highly flexible) do not have the necessary rotational
positioning capability. Another limitation of many aneurysm
bridging devices described in the prior art is the poor
flexibility. Cerebral blood vessels are tortuous and a high degree
of flexibility is required for effective delivery to most aneurysm
locations in the brain.
[0009] What has been needed are devices and methods for delivery
and use in small and tortuous blood vessels that can substantially
block the flow of blood into an aneurysm, such as a cerebral
aneurysm. In addition, what has been needed are methods and devices
suitable for blocking blood flow in cerebral aneurysms over an
extended period of time without a significant risk of deformation,
compaction or dislocation.
SUMMARY
[0010] In one embodiment of the invention, a device for removal of
thrombus from a blood vessel is described. The device includes an
expandable cylindrical structure having a proximal end and a distal
end, and being formed from a plurality of wires, wherein adjacent
wires are engaged to each other by a plurality of twists. The
plurality of wires is secured together at the distal end and the
proximal end of the cylindrical structure. The cylindrical
structure has a radially constrained state and an expanded relaxed
state. The device also includes a self-expanding resilient
permeable shell having a proximal end, a distal end, and a
longitudinal axis. The self-expanding resilient permeable shell
includes a plurality of elongate resilient filaments having a
braided structure with a plurality of openings, wherein the
plurality of filaments is secured at proximal and distal ends. The
self-expanding permeable shell has a radially constrained elongated
state and an expanded relaxed state with a globular, axially
shortened configuration relative to the radially constrained state.
The self-expanding permeable shell is enclosed within the
expandable cylindrical structure and positioned at the distal end
of the expandable cylindrical structure.
[0011] In another embodiment of the invention, a method for
removing a thrombus having a proximal and distal end from a blood
vessel, is described. A thrombus removal device is obtained. The
thrombus removal device includes an expandable cylindrical
structure having a proximal end, a middle portion, and a distal
end. The expandable cylindrical structure is formed from a
plurality of wires, wherein adjacent wires are engaged to each
other by a plurality of twists, the plurality of wires secured
together at distal ends and secured together at proximal ends. The
cylindrical structure has a radially constrained state and an
expanded relaxed state. The thrombus removal device also includes a
self-expanding resilient permeable shell having a proximal end, a
distal end, and a longitudinal axis. The self-expanding resilient
permeable shell includes a plurality of elongate resilient
filaments having a braided structure with a plurality of openings,
wherein the plurality of filaments is secured at proximal and
distal ends. The self-expanding permeable shell has a radially
constrained elongated state and an expanded relaxed state with a
globular, axially shortened configuration relative, to the radially
constrained state. The self-expanding permeable shell is enclosed
within the expandable cylindrical structure and positioned at the
distal end of the expandable cylindrical structure. The thrombus
removal device is slideably positioned within a microcatheter and
the microcatheter is inserted into the patient, the expandable
cylindrical structure and self-expanding resilient permeable shell
both being in the radially constrained state within the
microcatheter. The distal end of the microcatheter is positioned
adjacent a distal end of the thrombus. The thrombus removal device
is deployed from the microcatheter by relative displacement of the
thrombus removal device and the microcatheter. Upon deployment, the
proximal end of the self-expanding resilient permeable shell
located within the expandable cylindrical structure is located
distal of the thrombus and the middle portion of the expandable
cylindrical structure overlaps the proximal and distal ends of the
thrombus, wherein the self-expanding resilient permeable shell and
the expandable cylindrical structure moves toward their expanded
states once the thrombus removal device is advanced out of the
microcatheter. The expandable expanded cylindrical structure with
the self-expanding resilient permeable shell at the distal end of
the cylindrical structure is then moved in a proximal direction,
thereby detaching the thrombus or thrombi from the endoluminal
surface of the vessel and capturing the thrombus in the expandable
cylindrical structure. The thrombus removal device and the captured
thrombus or thrombi are then removed from the blood vessel.
[0012] The thrombus removal device and the microcatheter may be
removed together from the blood vessel. Alternatively, the thrombus
removal device may be removed from the microcatheter and the
microcatheter may be left in place in the blood vessel. The
thrombus removal device and the microcatheter may be removed
together from the patient. Alternatively, the thrombus removal
device may be removed from the microcatheter and the microcatheter
may be left in place in the patient. The self-expanding permeable
shell may have a braid density sufficiently high to maintain the
thrombus within the cylindrical structure and also allow blood to
flow through the self-expanding permeable shell.
[0013] In another embodiment of the invention, a device for
treatment of an aneurysm is described. The device includes a distal
self-expanding resilient permeable shell having a proximal end, a
distal end, and a longitudinal axis. The distal permeable shell
includes a plurality of elongate resilient filaments having a
braided structure with a plurality of openings formed between the
braided filaments. The plurality of filaments is gathered at least
at the proximal end thereof. The distal permeable shell has a
radially constrained elongated state configured for delivery within
a microcatheter and an expanded state with an axially shortened
configuration relative to the radially constrained state, wherein
the expanded state of the distal permeable shell has a convex shape
at the distal end of the distal permeable shell. The device also
includes a proximal self-expanding resilient permeable shell having
a proximal end, a distal end, and a longitudinal axis. The proximal
permeable shell includes a plurality of elongate resilient
filaments having a braided structure with a plurality of openings
formed between the braided filaments. The plurality of filaments is
gathered at least at the proximal end thereof. The proximal
permeable shell has a radially constrained elongated state
configured for delivery within a microcatheter and an expanded
state with an axially shortened configuration relative to the
radially constrained state, wherein the expanded state of the
proximal permeable shell has a generally convex shape at the
proximal end of the proximal permeable shell. The device also
includes an elongate support member having a proximal end and a
distal end. The elongate support member is positioned between the
distal and proximal permeable shells. The expanded states of the
distal and proximal permeable shells define a toroidal cavity
through which the elongate support member extends.
[0014] The average size of the plurality of openings in the distal
permeable shell may be larger than an average size of the plurality
of openings in the proximal permeable shell. The average size of
the plurality of openings in the distal permeable shell may be
about 300 .mu.m to about 900 .mu.m, alternatively about 300 .mu.m
to about 700 .mu.m, alternatively 300 .mu.m to about 500 .mu.m. The
average size of the plurality of openings in the proximal permeable
shell may be about 50 .mu.m to about 200 .mu.m, alternatively about
100 .mu.m to about 200 .mu.m, or alternatively about 50 .mu.m to
about 150 .mu.m. The braided structure of the distal permeable
shell may have a first braid density and the braided structure of
the proximal permeable shell may have a second braid density. The
first braid density may be greater than the second braid density.
The first braid density may be between about 0.10 and 0.20, or
alternatively between about 0.10 and 0.15. The second braid density
may be between about 0.15 and 0.40, alternatively between about
0.17 and 0.30.
[0015] The elongate support member may be rigid or it may be a
coil. If the elongate support member is rigid, it may be formed
from a hypo tube. If the elongate support member is a coil, it may
be an extension spring. At rest, the extension spring is not
compressible to a smaller length. The elongate support member may
have a length between about 2 mm and about 10 mm, alternatively
between about 3 mm and about 8 mm, or alternatively between about
3.5 mm and about 5.5 mm. The extension spring may have a length
between about 2 mm and about 10 alternatively between about 3 mm
and about 8 mm, and alternatively between about 3.5 mm and about
5.5 mm. The rigid support member may have a length between about 2
mm and about 10 mm, alternatively between about 3 mm and about 8
mm, or alternatively between about 3.5 mm and about 5.5 mm.
[0016] The plurality of filaments that make up the distal and
proximal permeable shells may include nitinol wires, drawn filled
tubes, and mixtures thereof. The plurality of filaments of the
distal permeable shell may be gathered at the distal end of the
distal permeable shell. Moreover, each of the plurality of
filaments of the distal permeable shell has a first end and a
second end. The first and second ends of the plurality of filaments
of the distal permeable shell may be gathered at the proximal end
of the distal permeable shell.
[0017] The expanded shape of the distal permeable shell may contact
the expanded shape of the proximal permeable shell. The expanded
shape of the distal permeable shell and the expanded shape of the
proximal permeable shell may also form a substantially globular
shape.
[0018] In another embodiment of the invention, a method for
treating a cerebral aneurysm is described. The method includes the
step of providing an implant having a distal self-expanding
resilient permeable shell, a proximal self-expanding resilient
permeable shell, and an elongate support member positioned between
the distal and proximal permeable shells. The distal self-expanding
resilient permeable shell has a proximal end, a distal end, and a
longitudinal axis, and includes a plurality of elongate resilient
filaments having a braided structure with a plurality of openings
formed between the braided filaments. The plurality of filaments
are gathered at least at the proximal end thereof, wherein the
distal permeable shell has a radially constrained elongated state
configured for delivery within a microcatheter and an expanded
state with an axially shortened configuration relative to the
radially constrained state, wherein the expanded state of the
distal permeable shell has a convex shape at the distal end of the
distal permeable shell.
[0019] In one embodiment of the invention, a device for treatment
of an aneurysm within a patient's vasculature is described. The
device includes a self-expanding resilient permeable shell having a
proximal end, a distal end, and a longitudinal axis. The shell is
made of a plurality of elongate resilient filaments having a
braided structure, wherein the plurality of filaments are secured
at least at one of the proximal end or the distal end thereof. The
permeable shell has a plurality of openings formed between the
braided filaments. The device also includes a metallic coil formed
from a wire having a first diameter. The metallic coil is secured
at the distal end of the self-expanding resilient permeable shell.
The permeable shell has a radially constrained elongated state
configured for delivery within a microcatheter and has an expanded
state with a globular, axially shortened configuration relative to
the radially constrained state. The metallic coil has a linear,
straightened shape configured for delivery within a microcatheter
and an expanded state having at least one loop having a secondary
diameter.
[0020] The metallic coil may be configured to place a bias on the
permeable shell when the permeable, shell is in the expanded state
within, an aneurysm. When at least partially compressed in an axial
direction, the metallic coil can apply an axial bias of at least
0.27 grams, alternatively at least 2.67 grams, alternatively at
least 16.6 grams, alternatively between about 0.27 grams and about
40 grams, alternatively between about 2.67 grams and about 30
grams, alternatively between about 16.6 grams and about 20
grams.
[0021] In another embodiment of the invention, methods for treating
a cerebral aneurysm are described. An implant structure is
provided. The implant structure includes a self-expanding resilient
permeable shell having a proximal end, a distal end, and a
longitudinal axis. The shell includes a plurality of elongate
resilient filaments having a braided structure, wherein the
plurality of filaments are secured at least at one of the proximal
end or the distal end thereof. The implant structure also includes
a metallic coil formed from a wire having a first diameter, wherein
the metallic coil is secured at the distal end of the
self-expanding resilient permeable shell. The permeable shell has a
plurality of openings formed between the braided filaments. The
device also includes a metallic coil formed from a wire having a
first diameter. The metallic coil is secured at the distal end of
the self-expanding resilient permeable shell. The permeable shell
has a radially constrained elongated state configured for delivery
within a microcatheter and has an expanded state with a globular,
axially shortened configuration relative to the radially
constrained state. The metallic coil has a linear, straightened
shape configured for delivery within a microcatheter and an
expanded state having at least one loop having a secondary
diameter. The implant is advanced within a microcatheter to a
region near the cerebral aneurysm. The implant is deployed within
the cerebral aneurysm such that the metallic coil is positioned
near a dome of the cerebral aneurysm and assumes the expanded
state, and the permeable shell assumes the expanded deployed state
within the cerebral aneurysm. The microcatheter is then withdrawn
from the region near the cerebral aneurysm after the implant is
deployed.
[0022] Once deployed in the cerebral aneurysm, the metallic coil
may push the permeable shell against an opening of the cerebral
aneurysm. The metallic coil may track around the diameter of the
cerebral aneurysm. The secondary diameter of the metallic coil may
approximately equal a diameter of the permeable shell. When at
least partially compressed, the metallic coil can apply an axial
bias of at least 0.27 grams, alternatively at least 2.67 grams,
alternatively at least 16.6 grams, alternatively between about 0.27
grams and about 40 grams, alternatively between about 2.67 grams
and about 30 grams, alternatively between about 16.6 grams and
about 20 grams.
[0023] In another embodiment of the invention, a device for
treatment of an aneurysm within a patient's vasculature is
described. The device includes a self-expanding resilient permeable
shell having a proximal end, a distal end, and a longitudinal axis.
The shell is made of a plurality of elongate resilient filaments
having a braided structure, wherein the plurality of filaments are
secured at least at one of the proximal end or the distal end
thereof. The permeable shell has a plurality of openings formed
between the braided filaments. The device also includes a force
biasing member secured at the distal end of the self-expanding
resilient permeable shell. The permeable shell has a radially
constrained elongated state configured for delivery within a
microcatheter and has an expanded state with a globular, axially
shortened configuration relative to the radially constrained state.
The force biasing member has a linear, straightened shape
configured for delivery within a microcatheter and an expanded
state after delivery from the microcatheter.
[0024] The force biasing member may be configured to place a bias
on the permeable shell when the permeable shell is in the expanded
state within an aneurysm. When at least partially compressed in an
axial direction, the metallic coil can apply an axial bias of at
least 0.27 grams, alternatively at least 2.67 grams, alternatively
at least 16.6 grams, alternatively between about 0.27 grams and
about 40 grams, alternatively between about 2.67 grams and about 30
grams, alternatively between about 16.6 grams and about 20 grams.
The force biasing member may be configured to conform to a
three-dimensional framing shape. The force biasing member may be
made from wire comprising platinum.
[0025] The force biasing member may also have a generally circular
shape. The plurality of filaments forming the permeable shell may
be secured at the distal end. A distal region of at least some of
the plurality of filaments extend beyond the distal end of the
permeable shell and form an extension having a generally circular
shape, which may be the force biasing member. The plurality of
filaments may be secured by a cylindrical hub having a proximal and
distal end, and the extension may extend from the distal end of the
cylindrical hub. The distal regions of filaments forming the
extension may be straight or braided or partially braided, or the
braid may be partially undone or unraveled.
[0026] In another embodiment of the invention, methods for treating
a cerebral aneurysm are described. An implant structure is
provided. The implant structure includes a self-expanding resilient
permeable shell having a proximal end, a distal end, and a
longitudinal axis. The shell includes a plurality of elongate
resilient filaments having a braided structure, wherein the
plurality of filaments are secured at least at one of the proximal
end or the distal end thereof. The device also includes a force
biasing member secured at the distal end of the self-expanding
resilient permeable shell. The permeable shell has a plurality of
openings formed between the braided filaments. The permeable shell
has a radially constrained elongated state configured for delivery
within a microcatheter and has an expanded state with a globular,
axially shortened configuration relative to the radially
constrained state. The force biasing member has a linear,
straightened shape configured for delivery within a microcatheter
and an expanded state after delivery from the microcatheter. The
implant is advanced within a microcatheter to a region near the
cerebral aneurysm. The implant is deployed within the cerebral
aneurysm such that the force biasing member is positioned near a
dome of the cerebral aneurysm and assumes the expanded state, and
the permeable shell assumes the expanded deployed state within the
cerebral aneurysm. The microcatheter is then withdrawn from the
region near the cerebral aneurysm after the implant is
deployed.
[0027] Once deployed in the cerebral aneurysm, the force biasing
member may push the permeable shell against en opening of the
cerebral aneurysm. When at least partially compressed in an axial
direction, the metallic coil can apply an axial bias of at least
0.27 grams, alternatively at least 2.67 grams, alternatively at
least 16.6 grams, alternatively between about 0.27 grams and about
40 grams, alternatively between about 2.67 grams and about 30
grams, alternatively between about 16.6 grams and about 20 grams.
The force biasing member may be configured to conform to a
three-dimensional framing shape. The force biasing member may be
made from wire comprising platinum.
[0028] In another embodiment, a device for treatment of an aneurysm
within a patient's vasculature is described. The device includes a
self-expanding resilient permeable shell having a proximal end, a
distal end, and a longitudinal axis. The shell includes a plurality
of elongate resilient filaments having a braided structure. The
plurality of filaments are secured at the distal end of the
permeable shell. Distal regions of at least some of the plurality
of filaments extend beyond the distal end of the permeability shell
and form an extension having a generally circular shape when
expanded. The plurality of filaments may be secured by a
cylindrical hub having a proximal and distal end, and the extension
may extend from the distal end of the cylindrical hub. The distal
regions of filaments forming the extension may be straight or
braided or partially braided, or the braid may be partially undone
or unraveled.
[0029] In another embodiment of the invention, methods for treating
a cerebral aneurysm are described. An implant structure is
provided. The implant structure includes a self-expanding resilient
permeable shell having a proximal end, a distal end, and a
longitudinal axis. The shell includes a plurality of elongate
resilient filaments having a braided structure. The plurality of
filaments are secured at the distal end of the permeable shell.
Distal regions of at least some of the plurality of filaments
extend beyond the distal end of the permeability shell and form an
extension having a generally circular shape when expanded. The
implant is advanced within a microcatheter to a region near the
cerebral aneurysm. The implant is deployed within the cerebral
aneurysm such that the extension is positioned near a dome of the
cerebral aneurysm and assumes the generally circular expanded
state, and the permeable shell assumes the expanded deployed state
within the cerebral aneurysm. The microcatheter is then withdrawn
from the region near the cerebral aneurysm after the implant is
deployed. The plurality of filaments may be secured by a
cylindrical hub having a proximal and distal end, and the extension
may extend from the distal end of the cylindrical hub. The distal
regions of filaments forming the extension may be straight or
braided or partially braided, or the braid may be partially undone
or unraveled.
BRIEF DESCRIPTION OF THE DRAWINGS
[0030] FIG. 1 is an elevation view of an embodiment of a device for
treatment of a patient's vasculature and a plurality of arrows
indicating inward radial force.
[0031] FIG. 2 is an elevation view of a beam supported try two
simple supports and a plurality of arrows indicating force against
the beam.
[0032] FIG. 3 is a bottom perspective view of an embodiment of a
device for treatment of a patient's vasculature.
[0033] FIG. 4 is an elevation view of the device for treatment of a
patient's vasculature of FIG. 3.
[0034] FIG. 5 is a transverse cross sectional view of the device of
FIG. 4 taken along lines 5-5 in FIG. 4.
[0035] FIG. 6 shows the device of FIG. 4 in longitudinal section
taken along lines 6-6 in FIG. 4.
[0036] FIG. 7 is an enlarged view of the woven filament structure
taken from the encircled portion 7 shown in FIG. 5.
[0037] FIG. 8 is an enlarged view of the woven filament structure
taken from the encircled portion 8 shown in FIG. 6.
[0038] FIG. 9 is a proximal end view of the device of FIG. 3.
[0039] FIG. 10 is a transverse sectional view of a proximal hub
portion of the device in FIG. 6 indicated by lines 10-10 in FIG.
6.
[0040] FIG. 11 is an elevation view in partial section of a distal
end of a delivery catheter with the device for treatment of a
patient's vasculature of FIG. 3 disposed therein in a collapsed
constrained state.
[0041] FIG. 12 is an elevation view of a distal portion of a
delivery device or actuator showing some internal structure of the
device.
[0042] FIG. 13 is an elevation view of the delivery device of FIG.
12 with the addition of some tubular elements over the internal
structures.
[0043] FIG. 14 is an elevation view of the distal portion of the
delivery device of FIG. 13 with an outer coil and marker in
place.
[0044] FIG. 15 is an elevation view of a proximal portion of the
delivery device.
[0045] FIG. 16 illustrates an embodiment of a filament
configuration for a device for treatment of a patient's
vasculature.
[0046] FIG. 17 is a schematic view of a patient being accessed by
an introducer sheath, a microcatheter and a device for treatment of
a patient's vasculature releasably secured to a distal end of a
delivery device or actuator.
[0047] FIG. 18 is a sectional view of a terminal aneurysm.
[0048] FIG. 19 is a sectional view of an aneurysm.
[0049] FIG. 20 is a schematic view in section of an aneurysm
showing perpendicular arrows that indicate anterior longitudinal
and transverse dimensions of the aneurysm.
[0050] FIG. 21 is a schematic view in section of the aneurysm of
FIG. 20 with a dashed outline of a device for treatment of a
patient's vasculature in a relaxed unconstrained state that extends
transversely outside of the walls of the aneurysm.
[0051] FIG. 22 is a schematic view in section of an outline of a
device represented by the dashed line in FIG. 21 in a deployed and
partially constrained state within the aneurysm.
[0052] FIGS. 23-26 show a deployment sequence of a device for
treatment of a patient's vasculature.
[0053] FIG. 27 is an elevation view of a mandrel used for
manufacture of a braided tubular member for construction of an
embodiment of a device for treatment of a patient's vasculature
with the initiation of the braiding process shown.
[0054] FIG. 28 is an elevation view of a braiding process for a
braided tubular member used for manufacture of a device.
[0055] FIG. 29 is an elevation view in partial section of an
embodiment of a fixture for heat setting a braided tubular member
for manufacture of a device for treatment of a patient's
vasculature.
[0056] FIG. 30 is an elevation view in partial section of an
embodiment of a fixture for heat setting a braided tubular member
for manufacture of a device for treatment of a patient's
vasculature.
[0057] FIG. 31 is an elevation view in section that illustrates a
flow of blood within an aneurysm of a patient's vasculature.
[0058] FIG. 32 is a perspective view in section of a of a composite
filament embodiment.
[0059] FIG. 33 is an elevation view of an embodiment of a device
for treatment of a patient's vasculature.
[0060] FIGS. 34A-34B illustrate a method of implanting a second
configuration of the embodiment of FIG. 33 within a vascular
defect.
[0061] FIGS. 35A-35B illustrate a method of implanting a third
configuration of the embodiment of FIG. 33 within a vascular
defect.
[0062] FIG. 35C illustrates an elevation view of an embodiment of a
device, for treatment of a patient's vasculature.
[0063] FIG. 35D illustrates a perspective view of a top of the
device of FIG. 35C.
[0064] FIGS. 35E-35F illustrate the device of FIG. 35C being
delivered from a microcatheter.
[0065] FIG. 36 is a partial cross-sectional view of an embodiment
of a mesh device.
[0066] FIG. 37 is a partial cross-sectional view of an embodiment
of a multi-lobe mesh device.
[0067] FIG. 38 is an elevation view in partial section of a distal
end of a delivery catheter with the device for treatment of a
patient's vasculature of FIG. 37 disposed therein in a collapsed
constrained state.
[0068] FIG. 39 is a partial cross-sectional view of an embodiment
of a multi-lobe mesh device.
[0069] FIG. 40 is a partial cross-section of the multi-lobe mesh
device of FIG. 37 in place in relation to a vascular defect.
[0070] FIG. 41 is a castellated mandrel assembly used in the
braiding process of the embodiments of devices for treatment of a
patient'vasculature.
[0071] FIG. 42 is a section view of the castellated mandrel
assembly of FIG. 41.
[0072] FIGS. 43A-43C illustrate the method of loading the
castellated mandrel assembly of FIG. 41 for the braiding process
for devices for treatment of a patient's vasculature.
[0073] FIG. 43D illustrates an alternative embodiment for loading
the castellated mandrel assembly of FIG. 41.
[0074] FIGS. 44A-44B illustrate the method of loading the
castellated mandrel assembly of FIG. 41 for the braiding process
for devices for treatment of a patient's vasculature.
[0075] FIG. 45 is an elevation view of an embodiment of a device
for treatment of a patient's vasculature.
[0076] FIG. 46 is an elevation view in partial section of a distal
end of a delivery catheter with the device for treatment of a
patient's vasculature of FIG. 45 disposed therein in a collapsed
constrained state.
[0077] FIG. 47 is the embodiment of a device for treatment of a
patient's vasculature of FIG. 45 deployed within an aneurysm.
[0078] FIG. 48 is an embodiment of a device for treatment of a
patient's vasculature deployed within an aneurysm.
[0079] FIG. 49 is an elevation view of an embodiment of a mesh
device prior to being longitudinally compressed.
[0080] FIG. 50 is an elevation view of the mesh device of FIG. 49
after a certain amount of longitudinal compression.
[0081] FIG. 51 is an elevation view of the mesh device of FIG. 49
after an additional amount of longitudinal compression.
[0082] FIG. 52 illustrates an embodiment of a system including a
multi-lobe mesh device.
[0083] FIGS. 53-56 illustrate the system of FIG. 5 being delivered
from a microcatheter.
[0084] FIG. 57A is an embodiment of a multi-lobe mesh device for
treatment of a patient's vasculature deployed within an
aneurysm.
[0085] FIG. 57B is a partially cut-away view of the multi-lobe mesh
device of FIG. 57A.
[0086] FIG. 57C is partial sectional view of the multi-lobe mesh
device of FIG. 57A.
[0087] FIG. 58 is a partially cut-away perspective view of the
multi-lobe mesh device of FIG. 57A.
[0088] FIG. 59 is an elevation view in partial section of a distal
end of a delivery catheter with the device for treatment of a
patient's vasculature of FIGS. 57A-58 disposed therein in a
collapsed constrained state.
[0089] FIG. 60 is a partially cut-away perspective view of an
embodiment of a multi-lobe mesh device.
[0090] FIG. 61 is a single diamond-shaped module in a multi-lobe
mesh device.
[0091] FIG. 62 is a perspective view of an embodiment of a
self-expanding device for removal of thrombus from a patient's
vasculature.
[0092] FIG. 63 is a detail view of the self-expanding device of
FIG. 62 taken within circle 63.
[0093] FIGS. 64-67 illustrate the thrombus removal device in use to
remove a thrombus from a blood vessel.
DETAILED DESCRIPTION
[0094] Discussed herein are devices and methods for the treatment
of vascular defects that are suitable for minimally invasive
deployment within a patient's vasculature, and particularly, within
the cerebral vasculature of a patient. For such embodiments to be
safely and effectively delivered to a desired treatment site and
effectively deployed, some device embodiments may be configured for
collapse to a low profile constrained state with a transverse
dimension suitable for delivery through an inner lumen of a
microcatheter and deployment from a distal end thereof. Embodiments
of these devices may also maintain a clinically effective
configuration with sufficient mechanical integrity once deployed so
as to withstand dynamic forces within a patient's vasculature over
time that may otherwise result in compaction of a deployed device.
It may also be desirable for some device embodiments to acutely
occlude a vascular defect of a patient during the course of a
procedure in order to provide more immediate feedback regarding
success of the treatment to a treating physician. Unless otherwise
stated, one or more of the features, dimensions, or materials of
the various embodiments may be used in other similar embodiments
discussed herein.
[0095] Some embodiments are particularly useful for the treatment
of cerebral aneurysms by reconstructing a vascular wall so as to
wholly or partially isolate a vascular defect from a patient's
blood flow. Some embodiments may be configured to be deployed
within a vascular defect to facilitate reconstruction, bridging of
a vessel wall or both in order to treat the vascular defect. For
some of these embodiments, a permeable shell of the device may be
configured to anchor or fix the permeable shell in a clinically
beneficial position. For some embodiments, the device may be
disposed in whole or in part within the vascular defect in order to
anchor or fix the device with respect to the vascular structure or
defect. The permeable shell may be configured to span an opening,
neck or other portion of a vascular defect in order to isolate the
vascular defect, or a portion thereof, from the patient's nominal
vascular system in order allow the defect to heal or to otherwise
minimize the risk of the defect to the patient's health.
[0096] For some or all of the embodiments of devices for treatment
of a patient's vasculature discussed herein, the permeable shell or
layer, or permeable shells or layers, of the device or devices may
be configured to allow some initial perfusion of blood through the
permeable shell or layer. The porosity of the permeable shell may
be configured to sufficiently isolate the vascular defect so as to
promote healing and isolation of the defect, but allow sufficient
initial flow through the permeable shell so as to reduce or
otherwise minimize the mechanical force exerted on the membrane the
dynamic flow of blood or other fluids within the vasculature
against the device. For some embodiments of devices for treatment
of a patient's vasculature, only a portion of the permeable shell
that spans the opening or neck of the vascular defect, sometimes
referred to as a defect spanning portion, need be permeable and/or
conducive to thrombus formation in a patient's bloodstream. For
such embodiments, that portion of the device that does not span an
opening or neck of the vascular defect may be substantially
non-permeable or completely permeable with a pore or opening
configuration that is too large to effectively promote thrombus
formation. In addition, a portion of the permeable shell that is
initially permeable or semi-permeable to blood flow may become
substantially non-permeable or completely non-permeable due to
thrombus formation on the filaments of the device. In some cases,
thrombus formation on filaments of the permeable shell or any other
portion of the device may serve to decrease the pore size between
the filaments or close off the pores of the permeable shell
completely.
[0097] In general, it may be desirable in some cases to use a
hollow, thin walled device with a permeable shell of resilient
material that may be constrained to a low profile for delivery
within a patient. Such a device may also be configured to expand
radially outward upon removal of the constraint such that the shell
of the device assumes a larger volume and fills or otherwise
occludes a vascular defect within which it is deployed. The outward
radial expansion of the shell may serve to engage some or all of an
Inner surface of the vascular defect whereby mechanical friction
between an outer surface of the permeable shell of the device and
the inside surface of the vascular defect effectively anchors the
device within the vascular defect. Some embodiments of such a
device may also be partially or wholly mechanically captured within
a cavity of a vascular defect, particularly where the defect has a
narrow neck portion with a larger interior volume. In order to
achieve a low profile and volume for delivery and be capable of a
high ratio of expansion by volume, some device embodiments include
a matrix of woven or braided filaments that are coupled together by
the interwoven structure so as to form a self-expanding permeable
shell having a pore or opening pattern between couplings or
intersections of the filaments that is substantially regularly
spaced and stable, while still allowing for conformity and
volumetric constraint.
[0098] As used herein, the terms woven and braided are used
interchangeably to mean any form of interlacing of filaments to
form a mesh structure. In the textile and other industries, these
terms may have different or more specific meanings depending on the
product or application such as whether an article is made in a
sheet or cylindrical form. For purposes of the present disclosure,
these terms are used interchangeably.
[0099] For some embodiments, three factors may be critical for a
woven or braided wire occlusion device for treatment of a patient's
vasculature that can achieve a desired clinical outcome in the
endovascular treatment of cerebral aneurysms. We have found that
for effective use in some applications, it may be desirable for the
implant device to have sufficient radial stiffness for stability,
limited pore size for near-complete acute (intra-procedural)
occlusion, and a collapsed profile that is small enough to allow
insertion through an inner lumen of a microcatheter. A device with
a radial stiffness below a certain threshold may be unstable and
may be at higher risk of undesired movement and embolization of the
wrong region of the vasculature in some cases. Larger pores between
filament intersections in a braided or woven structure may not
generate thrombus and occlude a vascular defect in an acute setting
and thus may not give a treating physician or health professional
such clinical feedback that the flow disruption will lead to a
complete and lasting occlusion of the vascular defect being
treated. Delivery of a device for treatment of a patient's
vasculature through a standard microcatheter may be highly
desirable to allow access through the tortuous cerebral vasculature
in the manner that a treating physician is accustomed.
[0100] For some embodiments, it may be desirable to use filaments
having two or more different diameters or transverse dimensions to
form a permeable shell in order to produce a desired configuration
as discussed in more detail below. The radial stiffness of a
two-filament (two different diameters) woven device may be
expressed as a function of the number of filaments and their
diameters, as follows:
S.sub.radial=(1.2.times.10.sup.6
lbf/D.sup.4)(N.sub.ld.sub.l.sup.4+N.sub.sd.sub.s.sup.4) [0101]
where S.sub.radial is the radial stiffness in pounds force (lbf),
[0102] D is the Device diameter (transverse dimension), [0103]
N.sub.l is the number of large filaments, [0104] N.sub.s is the
number of small filaments, [0105] d.sub.l is the diameter of the
large filaments in inches, and [0106] d.sub.s is the diameter of
the small filaments in inches.
[0107] Using this expression, the radial stiffness S.sub.radial may
be between about 0.014 and about 0.284 lbf force for some
embodiments of particular clinical value. In some embodiments, the
radial stiffness S.sub.radial may be between about 0.015 and about
0.065 lbf. In some embodiments, the radial stiffness S.sub.radial
may be measured at a deformation of about 50%.
[0108] The maximum pore size in a portion of a device that spans a
neck or opening of a vascular defect desirable for some useful
embodiments of a woven wire device for treatment of a patient's
vasculature may be expressed as a function of the total number of
all filaments, filament diameter and the device diameter. The
difference between filament sizes where two or more filament
diameters or transverse dimensions are used may be ignored in some
cases for devices where the filament size(s) are very small
compared to the device dimensions. For a two-filament device, i.e.,
a device made from filaments of two different sizes, the smallest
filament diameter may be used for the calculation. Thus, the
maximum pore size for such embodiments may be expressed as
follows:
P.sub.max=(1.7/N.sub.T)(.pi.D-(N.sub.Td.sub.w/2)) [0109] where
P.sub.max is the average pore size, [0110] D is the Device diameter
(transverse dimension), [0111] N.sub.T is the total number of all
filaments, and [0112] d.sub.w is the diameter of the filaments
(smallest) in inches.
[0113] Using this expression, the maximum pore size, P.sub.max, of
a portion of a device that spans an opening of a vascular defect or
neck, or any other suitable portion of a device, may be less than
about 0.016 inches or about 400 microns for some embodiments. In
some embodiments the maximum pore size for a defect spanning
portion or any other suitable portion of a device may be less than
about 0.012 inches or about 300 microns. In some embodiments, the
maximum pore size for a defect spanning portion or any other
suitable portion of a device may be less than about 0.008 inches or
about 200 microns.
[0114] The collapsed profile of a two-filament (profile having two
different filament diameters) woven filament device may be
expressed as the function:
P.sub.c=1.48((N.sub.ld.sub.l.sup.2+N.sub.sd.sub.s2)).sup.1/2 [0115]
where P.sub.c is the collapsed profile of the device, [0116]
N.sub.l is the number of large filaments, [0117] N.sub.s is the
number of small filaments, [0118] d.sub.l is the diameter of the
large filaments in inches, and [0119] d.sub.s is the diameter of
the small filaments in inches.
[0120] Using this expression, the collapsed profile Pc may be less
than about 1.0 mm for some embodiments of particular clinical
value. In some embodiments of particular clinical value, the device
may be constructed so as to have all three factors (S.sub.radial,
P.sub.max and P.sub.c) above within the ranges discussed above;
S.sub.radial between about 0.014 lbf and about 0.284 lbf, or
between about 0.015 lbf and about 0.065 lbf, P.sub.max less than
about 300 microns and P.sub.c less than about 1.0 mm,
simultaneously. In some such embodiments, the device may be made to
include about 70 filaments to about 300 filaments. In some cases,
the filaments may have an outer transverse dimension or diameter of
about 0.0004 inches to about 0.002 inches. In some cases the
filaments may have an outer transverse dimension or diameter of
about 0.0005 inches to about 0.0015 inches. In some cases the
filaments may have an outer transverse dimension or diameter of
about 0.00075 inches to about 0.00125 inches.
[0121] As has been discussed, some embodiments of devices for
treatment of a patient's vasculature call for sizing the device
which approximates (or with some over-sizing) the vascular site
dimensions to fill the vascular site. One might assume that scaling
of a device to larger dimensions and using larger filaments would
suffice for such larger embodiments of a device. However, for the
treatment of brain aneurysms, the diameter or profile of the
radially collapsed device is limited by the catheter sizes that can
be effectively navigated within the small, tortuous vessels of the
brain. Further, as a device is made larger with a given or fixed
number of resilient filaments having a given size or thickness, the
pores or openings between junctions of the filaments become
correspondingly larger. In addition, for a given filament size the
flexural modulus or stiffness of the filaments and thus the
structure decrease with increasing device dimension. Flexural
modulus may be defined as the ratio of stress to strain. Thus, a
device may be considered to have a high flexural modulus or be
stiff if the strain (deflection) is low under a given force. A
stiff device may also be said to have low compliance.
[0122] To properly configure larger size devices for treatment of a
patient's vasculature, it may be useful to model the force on a
device when the device is deployed into a vascular site or defect,
such as a blood vessel or aneurysm, that has a diameter or
transverse dimension that is smaller than a nominal diameter or
transverse dimension of the device in a relaxed unconstrained
state. As discussed, it may be advisable to "over-size" the device
in some cases so that there is a residual force between an outside
surface of the device and an inside surface of the vascular wall.
The inward radial force on a device 10 that results from
over-sizing is illustrated schematically in FIG. 1 with the arrows
12 in the figure representing the inward radial force. As shown in
FIG. 2, these compressive forces on the filaments 14 of the device
in FIG. 1 can be modeled as a simply supported beam 16 with a
distributed load or force as shown by the arrows 18 in the figure.
It can be seen from the equation below for the deflection of a beam
with two simple supports 20 and a distributed load that the
deflection is a function of the length, L to the 4th power:
Deflection of Beam.times.5FL.sup.4/384 EI [0123] where F=force,
[0124] L=length of beam, [0125] E=Young's Modulus, and [0126]
I=moment of inertia.
[0127] Thus, as the size of the device increases and L increases,
the compliance increases substantially. Accordingly, an outward
radial force exerted by an outside surface of the filaments 14 of
the device 10 against a constraining force when inserted into a
vascular site such as blood vessel or aneurysm is lower for a given
amount of device compression or over-sizing. This force may be
important in some applications to assure device stability and to
reduce the risk of migration of the device and potential distal
embolization.
[0128] In some embodiments, a combination of small and large
filament sizes may be utilized to make a device with a desired
radial compliance and yet have a collapsed profile that is
configured to fit through an inner lumen of commonly used
microcatheters. A device fabricated with even a small number of
relatively large filaments 14 can provide reduced radial compliance
(or increased stiffness) compared to a device made with all small
filaments. Even a relatively small number of larger filaments may
provide a substantial increase in bending stiffness due to change
in the moment of Inertia that results front an increase in diameter
without increasing the total cross sectional area of the filaments.
The moment of inertia (I) of a round wire of filament may be
defined by the equation:
I=.pi.d.sup.4/64 [0129] where d is the diameter of the wire or
filament.
[0130] Since the moment of inertia is a function of filament
diameter to the fourth power, a small change in the diameter
greatly increases the moment of inertia. Thus, a small change in
filament size can have substantial impact on the deflection at a
given load and thus the compliance of the device.
[0131] Thus, the stiffness can be increased by a significant amount
without a large increase in the cross sectional area of a collapsed
profile of the device 10. This may be particularly important as
device embodiments are made larger to treat large aneurysms. While
large cerebral aneurysms may be relatively rare, they present an
important therapeutic challenge as some embolic devices currently
available to physicians have relatively poor results compared to
smaller aneurysms.
[0132] As such, some embodiments of devices for treatment of a
patient's vasculature may be formed using a combination of
filaments 14 with a number of different diameters such as 2, 3, 4,
5 or more different diameters or transverse dimensions. In device
embodiments where filaments with two different diameters are used,
some larger filament embodiments may have a transverse dimension of
about 0.001 inches to about 0.004 inches and some small filament
embodiments may have a transverse dimension or diameter of about
0.0004 inches and about 0.0015 inches, more specifically, about
0.0004 inches to about 0.001 inches. Some structures may use
filaments having a transverse dimension of up to about 0.001
inches. The ratio of the number of large filaments to the number of
small filaments may be between about 2 and 12 and may also be
between about 4 and 8. In some embodiments, the difference in
diameter or transverse dimension between the larger and smaller
filaments may be less than about 0.004 inches, more specifically,
less than about 0.0035 inches, and even more specifically, less
than about 0.002 inches. As discussed generally above, it may not
always be necessary for all wires of filaments to meet the
parameters for the various relationships discussed herein. This may
be particularly true where relatively large numbers of filaments
are being used for a distinct structure. In some cases, a
filamentary structure may meet the relationship constraints
discussed herein where the predominance of filaments of a permeable
shell or inner structure meet a size constraint.
[0133] As discussed above, device embodiments 10 for treatment of a
patient's vasculature may include a plurality of wires, fibers,
threads, tubes or other filamentary elements that form a structure
that serves as a permeable shell. For some embodiments, a globular
shape may be formed from such filaments by connecting or securing
the ends of a tubular braided structure. For such embodiments, the
density of a braided or woven structure may inherently increase at
or near the ends where the wires or filaments 14 are brought
together and decrease at or near a middle portion 30 disposed
between a proximal end 32 and distal end 34 of the permeable shell
40.
[0134] For some embodiments, an end or any other suitable portion
of a permeable shell 40 may be positioned in an opening or neck of
a vascular defect such as an aneurysm for treatment. As such, a
braided or woven filamentary device with a permeable shell may not
require the addition of a separate defect spanning structure having
properties different from that of a nominal portion of the
permeable shell to achieve hemostasis and occlusion of the vascular
defect. Such a filamentary device may be fabricated by braiding,
weaving or other suitable filament fabrication techniques. Such
device embodiments may be shape set into a variety of three
dimensional shapes such as discussed herein.
[0135] Referring to FIGS. 3-10, an embodiment of a device for
treatment of a patient's vasculature 10 is shown. The device 10
includes a self-expanding resilient permeable shell 40 having a
proximal end 32, a distal end 34, a longitudinal axis 46 and
further comprising a plurality of elongate resilient filaments 14
including large filaments 48 and small filaments 50 of at least two
different transverse dimensions as shown in more detail in FIGS, 5.
7 and 18. The filaments 14 have a woven structure and are secured
relative to each other at proximal ends 60 and distal ends 62
thereof. The permeable shell 40 of the device has a radially
constrained elongated state configured for delivery within a
microcatheter 61, as shown in FIG. 11, with the thin woven
filaments 14 extending longitudinally from the proximal end 42 to
the distal end 44 radially adjacent each other along a length of
the filaments.
[0136] As shown in FIGS. 3-6, the permeable shell 40 also has an
expanded relaxed state with a globular and longitudinally shortened
configuration relative to the radially constrained state. In the
expanded state, the woven filaments 14 form the self-expanding
resilient permeable shell 40 in a smooth path radially expanded
from a longitudinal axis 46 of the device between the proximal end
32 and distal end 34. The woven structure of the filaments 14
includes a plurality of openings 64 in the permeable shell 40
formed between the woven filaments. For some embodiments, the
largest of said openings 64 may be configured to allow blood flow
through the openings only at a velocity below a thrombotic
threshold velocity. Thrombotic threshold velocity has been defined,
at least by some, as the time average velocity at which more than
50% of a vascular graft surface is covered by thrombus when
deployed within a patients vasculature. In the context of aneurysm
occlusion, a slightly different threshold may be appropriate.
Accordingly, the thrombotic threshold velocity as used herein shall
include the velocity at which clotting occurs within or on a
device, such as device 10, deployed within a patient's vasculature
such that blood flow into a vascular defect treated by the device
is substantially blocked in less than about 1 hour or otherwise
during the treatment procedure. The blockage of blood flow into the
vascular defect may be indicated in some cases by minimal contrast
agent entering the vascular defect after a sufficient amount of
contrast agent has been injected into the patent's vasculature
upstream of the implant site and visualized as it dissipates from
that site. Such sustained blockage of flow within less than about 1
hour or during the duration of the implantation procedure may also
be referred to as acute occlusion of the vascular defect.
[0137] As such, once the device 10 is deployed, any blood flowing
through the permeable shell may be slowed to a velocity below the
thrombotic threshold velocity and thrombus will begin to form on
and around the openings in the permeable shell 40. Ultimately, this
process may be configured to produce acute occlusion of the
vascular defect within which the device 10 is deployed. For some
embodiments, at least the distal end of the permeable shell 40 may
have a reverse bend in an everted configuration such that the
secured distal ends 62 of the filaments 14 are withdrawn axially
within the nominal permeable shell structure or contour in the
expanded state. For some embodiments, the proximal end of the
permeable shell further includes a reverse bend in an everted
configuration such that the secured proximal ends 60 of the
filaments 14 are withdrawn axially within the nominal permeable
shell structure 40 in the expanded state. As used herein, the term
everted may include a structure that is everted, partially everted
and/or recessed with a reverse bend as shown in the device
embodiment of FIGS. 3-6. For such embodiments, the ends 60 and 62
of the filaments 14 of the permeable shell or hub structure
disposed around the ends may be withdrawn within or below the
globular shaped periphery of the permeable shell of the device.
[0138] The elongate resilient filaments 14 of the permeable shell
40 may be secured relative to each other at proximal ends 60 and
distal ends 62 thereof by one or more methods including welding,
soldering, adhesive bonding, epoxy bonding or the like. In addition
to the ends of the filaments being secured together, a distal hub
66 may also be secured to the distal ends 62 of the thin filaments
14 of the permeable shell 40 and a proximal hub 68 secured to the
proximal ends 60 of the thin filaments 14 of the permeable shell
40. The proximal hub 68 may include a cylindrical member that
extends proximally beyond the proximal ends 60 of the thin
filaments so as to form a cavity 70 within a proximal portion of
the proximal hub 68. The proximal cavity 70 may be used for holding
adhesives such as epoxy, solder or any other suitable bonding agent
for securing an elongate detachment tether 72 that may in turn be
detachably secured to a delivery apparatus such as is shown in
FIGS. 11-15.
[0139] For some embodiments, the elongate resilient filaments 14 of
the permeable shell 40 may have a transverse cross section that is
substantially round in shape and be made from a superelastic
material that may also be a shape memory metal. The shape memory
metal of the filaments of the permeable shell 40 may be heat set in
the globular configuration of the relaxed expanded state as shown
in FIGS. 3-6. Suitable superelastic shape memory metals may include
alloys such as NiTi alloy and the like. The superelastic properties
of such alloys may be useful in providing the resilient properties
to the elongate filaments 14 so that they can be heat set in the
globular on shown, fully constrained for delivery within an inner
lumen of a microcatheter and then released to self-expand back to
substantially the original heat set shape of the globular
configuration upon deployment within a patient's body.
[0140] The device 10 may have an evened filamentary structure with
a permeable shell 40 having a proximal end 32 and a distal end 34
in an expanded relaxed state. The permeable shell 40 has a
substantially enclosed configuration for the embodiments shown.
Some or all of the permeable shell 40 of the device 10 may be
configured to substantially block or impede fluid flow or pressure
into a vascular defect or otherwise isolate the vascular defect
over some period of time after the device is deployed in an
expanded state. The permeable shell 40 and device 10 generally also
has a low profile, radially constrained state, as shown in FIG. 11,
with an elongated tubular or cylindrical configuration that
includes the proximal end 32, the distal end 34 and a longitudinal
axis 46. While in the radially constrained state, the elongate
flexible filaments 14 of the permeable shell 40 may be disposed
substantially parallel and in close lateral proximity to each other
between the proximal end and distal end forming a substantially
tubular or compressed cylindrical configuration.
[0141] Proximal ends 60 of at least some of the filaments 14 of the
permeable shell 40 may be secured to the proximal hub 68 and distal
ends 62 of at least some of the filaments 14 of the permeable shell
40 are secured to the distal hub 66, with the proximal hub 68 and
distal hub 66 being disposed substantially concentric to the
longitudinal axis 46 as shown in FIG. 4. The ends of the filaments
14 may be secured to the respective hubs 66 and 68 by any of the
methods discussed above with respect to securement of the filament
ends to each other, including the use of adhesives, solder, welding
and the like. A middle portion 30 of the permeable shell 40 may
have a first transverse dimension with a low profile suitable for
delivery from a microcatheter as shown in FIG. 11. Radial
constraint on the device 10 may be applied by an inside surface of
the inner lumen of a microcatheter, such as the distal end portion
of the microcatheter 61 shown, or it may be applied by any other
suitable mechanism that may be released in a controllable manner
upon ejection of the device 10 from the distal end of the catheter.
In FIG. 11 a proximal end or hub 68 of the device 10 is secured to
a distal end of an elongate delivery apparatus 110 of a delivery
system 112 disposed at the proximal hub 68 of the device 10.
[0142] Some device embodiments 10 having a braided or woven
filamentary structure may be formed using about 10 filaments to
about 300 filaments 14, more specifically, about 10 filaments to
about 100 filaments 14, and even more specifically, about 60
filaments to about 80 filaments 14. Some embodiments of a permeable
shell 40 may include about 70 filaments to about 300 filaments
extending from the proximal end 32 to the distal end 34, more
specifically, about 100 filaments to about 200 filaments extending
from the proximal end 32 to the distal end 34. For some
embodiments, the filaments 14 may have a transverse dimension or
diameter of about 0.0008 inches to about 0.004 inches. The elongate
resilient filaments 14 in some cases may have an outer transverse
dimension or diameter of about 0.0005 inch to about 0.005 inch,
more specifically, about 0.001 inch to about 0.003 inch, and in
some cases about 0.0004 inches to about 0.002 inches. For some
device embodiments 10 that include filaments 14 of different sizes,
the large filaments 48 of the permeable shell 40 may have a
transverse dimension or diameter that is about 0.001 inches to
about 0.004 inches and the small filaments 50 may have a transverse
dimension or diameter of about 0.0004 inches to about 0.0015
inches, more specifically, about 0.0004 inches to about 0.001
inches. In addition, a difference in transverse dimension or
diameter between the small filaments 50 and the large filaments 48
may be less than about 0.004 inches, more specifically, less than
about 0.0035 inches, and even more specifically, less than about
0.002 inches. For embodiments of permeable shells 40 that include
filaments 14 of different sizes, the number of small filaments 50
of the permeable shell 40 relative to the number of large filaments
48 of the permeable shell 40 may be about 2 to 1 to about 15 to 1,
more specifically, about 2 to 1 to about 12 to 1, and even more
specifically, about 4 to 1 to about 8 to 1.
[0143] The expanded relaxed state of the permeable shell 40, as
shown in FIG. 4, has an axially shortened configuration relative to
the constrained state such that the proximal hub 68 is disposed
closer to the distal hub 66 than in the constrained state. Both
hubs 66 and 68 are disposed substantially concentric to the
longitudinal axis 46 of the device and each filamentary element 14
forms a smooth arc between the proximal and distal hubs 66 and 68
with a reverse bend at each end. A longitudinal spacing between the
proximal and distal hubs 66 and 68 of the permeable shell 40 in a
deployed relaxed state may be about 25 percent to about 75 percent
of the longitudinal spacing between the proximal and distal hubs 66
and 68 in the constrained cylindrical state, for some embodiments.
The arc of the filaments 14 between the proximal and distal ends 32
and 34 may be configured such that a middle portion of each
filament 14 has a second transverse dimension substantially greater
than the first transverse dimension.
[0144] For some embodiments, the permeable shell 40 may have a
first transverse dimension in a collapsed radially constrained
state of about 0.2 mm to about 2 mm and a second transverse
dimension in a relaxed expanded state of about 4 mm to about 30 mm.
For some embodiments, the second transverse dimension of the
permeable shell 40 in an expanded state may be about 2 times to
about 150 times the first transverse dimension, more specifically,
about 10 times to about 25 times the first or constrained
transverse dimension. A longitudinal spacing between the proximal
end 32 and distal end 34 of the permeable shell 40 in the relaxed
expanded state may be about 25% percent to about 75% percent of the
spacing between the proximal end 32 and distal end 34 in the
constrained cylindrical state. For some embodiments, a major
transverse dimension of the permeable shell 40 in a relaxed
expanded state may be about 4 mm to about 30 mm, more specifically,
about 9 mm to about 15 mm, and even more specifically, about 4 mm
to about 8 mm.
[0145] An arced portion of the filaments 14 of the permeable shell
40 may have a sinusoidal-like shape with a first or outer radius 88
and a second or inner radius 90 near the ends of the permeable
shell 40 as shown in FIG. 6. This sinusoid-like or multiple curve
shape may provide a concavity in the proximal end 32 that may
reduce an obstruction of flow in a parent vessel adjacent a
vascular defect. For some embodiments, the first radius 88 and
second radius 90 of the permeable shell 40 may be between about
0.12 mm to about 3 mm. For some embodiments, the distance between
the proximal end 32 and distal end 34 may be less than about 60% of
the overall length of the permeable shell 40 for some embodiments.
Such a configuration may allow for the distal end 34 to flex
downward toward the proximal end 32 when the device 10 meets
resistance at the distal end 34 and thus may provide longitudinal
conformance. The filaments 14 may be shaped in some embodiments
such that there are no portions that are without curvature over a
distance of more than about 2 mm. Thus, for some embodiments, each
filament 14 may have a substantially continuous curvature. This
substantially continuous curvature may provide smooth deployment
and may reduce the risk of vessel perforation. For some
embodiments, one of the ends 32 or 34 may be retracted or everted
to a greater extent than the other so as to be more longitudinally
or axially conformal than the other end.
[0146] The first radius 88 and second radius 90 of the permeable
shell 40 may be between about 0.12 mm to about 3 mm for some
embodiments. For some embodiments, the distance between the
proximal end 32 and distal end 34 may be more than about 60% of the
overall length of the expanded permeable shell 40. Thus, the
largest longitudinal distance be the inner surfaces may be about
60% to about 90% of the longitudinal length of the outer surfaces
or the overall length of device 10. A gap between the hubs 66 and
68 at the proximal end 32 and distal end 34 may allow for the
distal hub 66 to flex downward toward the proximal hub 68 when the
device 10 meets resistance at thee distal end and thus provides
longitudinal conformance. The filaments 14 may be shaped such that
there are no portions that are without curvature over a distance of
more than about 2 mm. Thus, of some embodiments, each filament 14
may have a substantially continuous curvature. This substantially
continuous curvature may provide smooth deployment and may reduce
the risk of vessel perforation. The distal end 34 may be retracted
or everted to a greater extent than the proximal end 32 such that
the distal end portion of the permeable shell 40 may be more
radially conformal than the proximal end portion. Conformability of
a distal end portion may provide better device conformance to
irregular shaped aneurysms or other vascular defects. A convex
surface of the device may flex inward forming a concave surface to
conform to curvature of a vascular site.
[0147] FIG. 10 shows an enlarged view of the filaments 14 disposed
within a proximal hub 68 of the device 10 with the filaments 14 of
two different sizes constrained and tightly packed by an outer ring
of the proximal hub 68. The tether member 72 may optionally be
disposed within a middle portion of the filaments 14 or within the
cavity 70 of the proximal hub 68 proximal of the proximal ends 60
of the filaments 14 as shown in FIG. 6. The distal end of the
tether 72 may be secured with a knot 92 formed in the distal end
thereof which is mechanically captured in the cavity 70 of the
proximal hub 68 formed by a proximal shoulder portion 94 of the
proximal hub 68. The knotted distal end 92 of the tether 72 may
also be secured by bonding or potting of the distal end of the
tether 72 within the cavity 70 and optionally amongst the proximal
ends 60 of the filaments 14 with mechanical compression, adhesive
bonding, welding, soldering, brazing or the like. The tether
embodiment 72 shown in FIG. 6 has a knotted distal end 92 potted in
the cavity of the proximal hub 68 with an adhesive. Such a tether
72 may be a dissolvable, severable or releasable tether that may be
part of a delivery apparatus 110 used to deploy the device 10 as
shown in FIG. 11 and FIGS. 23-26. FIG. 10 also shows the large
filaments 48 and small filaments 50 disposed within and constrained
by the proximal hub 68 that may be configured to secure the large
and small filaments 48 and 50 in place relative to each other
within the outer ring of the proximal hub 68.
[0148] FIGS. 7 and 8 illustrate some configuration embodiments of
braided filaments 14 of a permeable shell 40 of the device 10 for
treatment of a patient's vasculature. The braid structure in each
embodiment is shown with a circular shape 100 disposed within a
pore 64 of a woven or braided structure with the circular shape 100
making contact with each adjacent filament segment. The pore
opening size may be determined at least in part by the size of the
filament elements 14 of the braid, the angle overlapping filaments
make relative to each other and the picks per inch of the braid
structure. For some embodiments, the cells or openings 64 may have
an elongated substantially diamond shape as shown in FIG. 7, and
the pores or openings 64 of the permeable shell 40 may have a
substantially more square shape toward a middle portion 30 of the
device 10, as shown in FIG. 8. The diamond shaped pores or openings
64 may have a length substantially greater than the width
particularly near the hubs 66 and 68. In some embodiments, the
ratio of diamond shaped pore or opening length to width may exceed
a ratio of 3 to 1 for some cells. The diamond-shaped openings 64
may have lengths greater than the width thus having an aspect
ratio, defined as Length/Width of greater than 1. The openings 64
near the hubs 66 and 68 may, have substantially larger aspect
ratios than those farther from the hubs as shown in FIG. 7. The
aspect ratio of openings 64 adjacent the hubs may be greater than
about 4 to 1. The aspect ratio of openings 64 near the largest
diameter may be between about 0.75 to 1 and about 2 to 1 for some
embodiments. For some embodiments, the aspect ratio of the openings
64 in the permeable shell 40 may be about 0.5 to 1 to about 2 to
1.
[0149] The pore size defined by the largest circular shapes 100
that may be disposed within openings 64 of the braided structure of
the permeable shell 40 without displacing or distorting the
filaments 14 surrounding the opening 64 may range in size from
about 0.005 inches to about 0.01 inches, more specifically, about
0.006 inches to about 0.009 inches, even more specifically, about
0.007 inches to about 0.008 inches for some embodiments. In
addition, at least some of the openings 64 formed between adjacent
filaments 14 of the permeable shell 40 of the device 10 may be
configured to allow blood flow through the openings 64 only at a
velocity below a thrombotic threshold velocity. For some
embodiments, the largest openings 64 in the permeable shell
structure 40 may be configured to allow blood flow through the
openings 64 only at a velocity below a thrombotic threshold
velocity. As discussed above, the pore size may be less than about
0.016 inches, more specifically, less than about 0.012 inches for
some embodiments. For some embodiments, the openings 64 formed
between adjacent filaments 14 may be about 0.005 inches to about
0.04 inches.
[0150] Referring to FIGS. 12-15, a delivery apparatus embodiment
110 of the delivery system 112 of FIG. 11 is shown in more detail.
The apparatus 110 includes an elongate colt wire 114 that extends
from a proximal end 116 of the apparatus 110 to a distal section
118 of the apparatus 110 as shown in FIG. 12. The core wire 114 is
configured to provide sufficient column strength to push a
constrained device 10 for treatment of a patient's vasculature
through an inner lumen 120 of the microcatheter 61 of the delivery
system 112 as shown in FIG. 11. The core wire 114 also has
sufficient tensile strength to withdraw or proximally retract the
device 10 from a position outside the microcatheter and axially
within the inner lumen 120 of the microcatheter 61. The tether 72
that extends proximally from the proximal hub 68 is secured to the
distal end of the core wire 114 with a length of shrinkable tubing
122 that is disposed over a portion of the tether 72 and a distal
section of the core wire 114 and shrunk over both as shown in FIG.
13, although any other suitable means of securement may be
used.
[0151] A heater coil 124 electrically coupled to a first conductor
126 and a second conductor 128 is disposed over a distal most
portion of the tether 72. The heater coil 124 may also be covered
with a length of polymer tubing 130 disposed over the beater coil
124 distal of the heat shrink tubing 122 that serves to act as a
heat shield and minimizes the leakage of heat from the heater coil
124 into the environment, such as the patient's blood stream,
around the delivery apparatus 110. Once the heat shrink tubing 122
and insulating polymer tubing 130 have been secured to the distal
section 118 of the apparatus 110, the proximal portion of the
tether 72 disposed proximal of the heat shrink tubing 122 may be
trimmed as shown in FIG. 13. An over coil 132 that extends from a
distal end 134 of the delivery apparatus 110 to a proximal section
136 of the apparatus 110 may then be disposed over the heater coil
124, core wire 114, tether 72, first conductor 126 and second
conductor 128 to hold these elements together, produce a low
friction outer surface and maintain a desired flexibility of the
delivery apparatus 110. The proximal section 136 of the apparatus
110 includes the proximal terminus of the over coil 132 which is
disposed distal of a first contact 13$ and second contact 140 which
are circumferentially disposed about the proximal section 136 of
the core wire 114, insulated therefrom, and electrically coupled to
the first conductor 126 and second conductor 128, respectively as
shown in FIG. 15.
[0152] The heater coil 124 may be configured to receive electric
current supplied through the first conductor 126 and second
conductor 128 from an electrical energy source 142 coupled to the
first contact 138 and second contact 140 at the proximal section
136 of the apparatus 110. The electrical current passed through the
heater coil 124 heats the heater coil to a temperature above the
melting point of the tether material 72 so as to melt the tether 72
and sever it upon deployment of the device 10.
[0153] Embodiments of the delivery apparatus 110 may generally have
a length greater than the overall length of a microcatheter 61 to
be used for the delivery system 112. This relationship allows the
delivery apparatus 110 to extend, along with the device 10 secured
to the distal end thereof, from the distal port of the inner lumen
120 of the microcatheter 61 while having sufficient length
extending from a proximal end 150 of the microcatheter 61, shown in
FIG. 17 discussed below, to enable manipulation thereof by a
physician. For some embodiments, the length of the delivery
apparatus 110 may be about 170 cm to about 200 cm. The core wire
114 may be made from any suitable high strength material such as
stainless steel, alloy, or the like. Embodiments of the core wire
114 may have an outer diameter or transverse dimension of about
0.010 inch to about 0.015 inch. The over coil 132 may have an outer
diameter or transverse dimension of about 0.018 inch to about 0.03
inch. Although the apparatus embodiment 110 shown in FIGS. 12-15 is
activated by electrical energy passed through a conductor pair, a
similar configuration that utilizes light energy passed through a
fiber optic or any other suitable arrangement could be used to
remotely heat a distal heating member or element such as the heater
coil 124 to sever the distal portion of the tether 72. In addition,
other delivery apparatus embodiments are discussed and incorporated
herein that may also be used for any of the device embodiments 10
for treatment of a patient's vasculature discussed herein.
[0154] Other delivery and positioning system embodiments may
provide for the ability to rotate a device for treatment of a
patient's vasculature in-vivo without translating torque along the
entire length of the delivery apparatus. Some embodiments for
delivery and positioning of devices 10 are described in co-owned
international PCT Patent Application No. PCT/US2008/065694. The
delivery and positioning apparatus may include a distal rotating
member that allows rotational positioning of the device. The
delivery and positioning apparatus may include a distal rotating
member that rotates an implant in-vivo without the transmission of
torque along the entire length of the apparatus. Optionally,
delivery system may also rotate the implant without the
transmission of torque in the intermediate portion between the
proximal end and the distal rotatable end. The delivery and
positioning apparatus may be releasably secured to any suitable
portion of the device for treatment of a patient's vasculature.
[0155] Device embodiments discussed herein may be releasable from
any suitable flexible, elongate delivery apparatus or actuator such
as a guidewire or guidewire-like structure. The release of device
embodiments from such a delivery apparatus may be activated by a
thermal mechanism, as discussed above, electrolytic mechanism,
hydraulic mechanism shape memory material mechanism, or any other
mechanism known in the art of endovascular implant deployment.
[0156] Embodiments for deployment and release of therapeutic
devices, such as deployment of embolic devices or stems within the
vasculature of a patient, may include connecting such a device via
a releasable connection to a distal portion of a pusher or other
delivery apparatus member. The therapeutic device 10 may be
detachably mounted to the distal portion of the apparatus by a
filamentary tether 72, string, thread, wire, suture, fiber, or the
like, which may be referred to above as the tether. The tether 72
may be in the form of a monofilament, rod, ribbon, hollow tube, or
the like. Some embodiments of the tether may have a diameter or
maximum thickness of between about 0.05 mm and 0.2 mm. The tether
72 may be configured to be able to withstand a maximum tensile load
of between about 0.5 kg and 5 kg. For some embodiments, due to the
mass of the device 10 being deployed which may be substantially
greater than some embolic devices, some known detachment devices
may lack sufficient tensile strength to be used for some
embodiments discussed herein. As such, it may be desirable to use
small very high strength fibers for some tether embodiments having
a "load at break" greater than about 15 Newtons. For some
embodiments, a tether made from a material known as Dyneema
Purity.RTM. available from Royal DSM, Heerlen, Netherlands may be
used.
[0157] The tether 72 may be severed by the input of energy such as
electric current to a heating element causing release of the
therapeutic device. For some embodiments, the heating element may
be a coil of wire with high electrical resistivity such as a
platinum-tungsten alloy. The tether member may pass through or be
positioned adjacent the heater element. The heater may be contained
substantially within the distal portion of the delivery apparatus
to provide thermal insulation to reduce the potential for thermal
damage to the surrounding tissues during detachment, in another
embodiment, current may pass through the tether that also acts as a
heating element.
[0158] Many materials may be used to make tether embodiments 72
including polymers, metals and composites thereof. One class of
materials that may be useful for tethers includes polymers such as
polyolefin, polyolefin elastomer such as polyethylene, polyester
(PET), polyamide (Nylon), polyurethane, polypropylene, block
copolymer such as PEBAX.RTM. or Hytrel.RTM., and ethylene vinyl
alcohol (EVA); or rubbery materials such as silicone, latex, and
Kraton. In some cases, the polymer may also be cross-linked with
radiation to manipulate its tensile strength and melt temperature.
Another class of materials that may be used for tether embodiment
may include metals such as nickel titanium alloy (Nitinol), gold,
platinum, tantalum and steel. Other materials that may be useful
for tether construction includes wholly aromatic polyester polymers
which are liquid crystal polymers (LCP) that may provide high
performance properties and are highly inert. A commercially
available LCP polymer is Vectran.RTM., which is produced by Kuraray
Co. (Tokyo, Japan). The selection of the material may depend on the
melting or softening temperature, the power used for detachment,
and the body treatment site. The tether may be joined to the
implant and/or the pusher by crimping, welding, knot tying,
soldering, adhesive bonding, or other means known in the art.
[0159] It should be noted also that many variations of filament and
proximal hub construction such as is detailed above with regard to
FIG. 10 may be used for useful embodiments of a device for
treatment of a patient's vasculature 10. FIG. 16 shows an enlarged
view in transverse cross section of a proximal hub configuration.
For the embodiment shown, the filaments 14 are disposed within a
proximal hub 68 or end portion of the device 10 with the filaments
14 constrained and tightly packed by an outer ring of the proximal
hub 68. A tether member 72 may be disposed within a middle portion
of the filaments 14 or within a cavity of the proximal hub 68
proximal of the proximal ends 60 of the filaments 14. Such a tether
72 may be a dissolvable, severable or releasable tether that may be
part of a release apparatus as discussed above used to deploy the
device.
[0160] FIG. 16 illustrates in transverse cross section an
embodiment of a proximal hub 68 showing the configuration of
filaments which may be tightly packed and radially constrained by
an inside surface of the proximal hub 68. In some embodiments, the
braided or woven structure of the permeable shell 40 formed from
such filaments 14 may be constructed using a large number of small
filaments. The number of filaments 14 may be greater than 125 and
may also be between about 80 filaments and about 180 filaments. As
discussed above, the total number of filaments 14 for some
embodiments may be about 70 filaments to about 300 filaments, more
specifically, about 100 filaments to about 200 filaments. In some
embodiments, the braided structure of the permeable shell 40 may be
constructed with two or more sizes of filaments 14. For example,
the structure may have several larger filaments that provide
structural support and several smaller filaments that provide the
desired pore size and density and thus flow resistance to achieve a
thrombotic threshold velocity in some cases. For some embodiments,
small filaments 50 of the permeable shell 40 may have a transverse
dimension or diameter of about 0.0006 inches to about 0.002 inches
for some embodiments and about 0.0004 inches to about 0.001 inches
in other embodiments. The large filaments 48 ma have a transverse
dimension or diameter of about 0.0015 inches to about 0.004 inches
in some embodiments and about 0.001 inches to about 0.004 inches in
other embodiments. The filaments 14 may be braided in a plain weave
that is one under, one over structure (shown in FIGS. 7 and 8) or a
supplementary weave; more than one warp interlace with one or more
than one weft. The pick count may be varied between about 25 and
200 picks per inch (PPI).
[0161] For some embodiments, the permeable shell 40 or portions
thereof may be porous and may be highly permeable to liquids. In
contrast to most vascular prosthesis fabrics or grafts which
typically have a water permeability below 2,000 ml/min/cm.sup.2
when measured at a pressure of 120 mmHg, the permeable shell 40 of
some embodiments discussed herein may have a water permeability
greater than about 2,000 ml/min/cm.sup.2, in some cases greater
than about 2,500 ml/min/cm.sup.2. For some embodiments, water
permeability of the permeable shell 40 or portions thereof may be
between about 2,000 and 10,000 ml/min/cm.sup.2, more specifically,
about 2,000 ml/min/cm.sup.2 to about 15,000 ml/min/cm.sup.2, when
measured at a pressure of 120 mmHg.
[0162] Device embodiments and components thereof may include
metals, polymers, biologic materials and composites thereof.
Suitable metals include zirconium-based alloys, cobalt-chrome
alloys, nickel-titanium alloys, platinum, tantalum, stainless
steel, titanium, gold, and tungsten. Potentially suitable polymers
include but are not limited to acrylics, silk, silicones, polyvinyl
alcohol, polypropylene, polyvinyl alcohol, polyesters polyethylene
terephthalate or PET), PolyEtherEther Ketone (PEEK),
polytetrafluoroethylene (PTFE), polycarbonate urethane (PCU) and
polyurethane (PU). Device embodiments may include a material that
degrades or is absorbed or eroded by the body. A bioresorbable
(e.g., breaks down and is absorbed by a cell, tissue, or other
mechanism within the body) or bioabsorbable (similar to
bioresorbable) material may be used. Alternatively, a bioerodable
erodes or degrades over time by contact with surrounding tissue
fluids, through cellular activity or other physiological
degradation mechanisms), biodegradable (e.g., degrades over time by
enzymatic or hydrolytic action, or other mechanism in the body), or
dissolvable material may be employed. Each of these terms is
interpreted to be interchangeable. Potentially suitable
bioabsorbable materials include polylactic acid (PLA),
poly(alpha-hydroxy acid) such as poly-L-lactide (PLLA),
poly-D-lactide (PDLA), polyglycolidc (PGA), polydioxanone,
polycaprolactone, polygluconate, polylactic acid-polyethylene oxide
copolymers, modified cellulose, collagen, poly(hydroxybutyrate),
polyanhydride, polyphosphoester, poly(amino acids), or related
copolymer materials. An absorbable composite fiber may be made by
combining a reinforcement fiber made from a copolymer of about 18%
glycolic acid and about 82% lactic acid with a matrix material
consisting of a blend of the above copolymer with about 20%
polycaprolactone (PCL).
[0163] In any of the suitable device embodiments 10 discussed
herein, the permeable shell structure 40, or any other suitable
permeable shell structure discussed herein, may include one or more
fixation elements or surfaces to facilitate fixation of the device
within a blood vessel or other vascular site. The fixation elements
may comprise hooks, barbs, protrusions, pores, micro-features,
texturing, bioadhesives or combinations thereof. Embodiments of the
support structure may be fabricated from a tube of metal where
portions are removed. The removal of material may be done by laser,
electrical discharge machining (EDM), photochemical etching and
traditional machining techniques. In any of the described
embodiments, the support structure may be constructed with a
plurality of wires, cut or etched from a sheet of a material, cut
or etched from a tube or a combination thereof as in the art of
vascular stent fabrication.
[0164] Permeable shell embodiments 40 may be formed at least in
part of wire, ribbon, or other filamentary elements 14. These
filamentary elements 14 may have circular, elliptical, ovoid,
square, rectangular, or triangular cross-sections. Permeable shell
embodiments 40 may also be formed using conventional machining,
laser cutting, electrical discharge machining (EDM) or
photochemical machining (PCM). If made of a metal, it may be formed
from either metallic tubes or sheet material. Permeable shell
embodiments 40 may be heat formed to maintain their shape. In some
embodiments, this may be done at a temperature of around
500.degree. C.
[0165] Device embodiments 10 discussed herein may be delivered and
deployed from a delivery and positioning system 112 that includes
microcatheter 61, such as the type of microcatheter 61 that is
known in the art of neurovascular navigation and therapy. Device
embodiments for treatment of a patient's vasculature 10 may be
elastically collapsed and restrained by a tube or other radial
restraint, such as an inner lumen 120 of a microcatheter 61, for
delivery and deployment. The microcatheter 61 may generally be
inserted through a small incision 152 accessing a peripheral blood
vessel such as the femoral artery or brachial artery. The
microcatheter 61 may be delivered or otherwise navigated to a
desired treatment site 154 from a position outside the patient's
body 156 over a guidewire 159 under fluoroscopy or by other
suitable guiding methods. The guidewire 159 may be removed during
such a procedure to allow insertion of the device 10 secured to a
delivery apparatus 110 of the delivery system 112 through the inner
lumen 120 of a microcatheter 61 in some cases. FIG. 17 illustrates
a schematic view of a patient 158 undergoing treatment of a
vascular defect 160 as shown in FIG. 18. An access sheath 162 is
shown disposed within either a radial artery 164 or femoral artery
166 of the patient 158 with a delivery system 112 that includes a
microcatheter 61 and delivery apparatus 110 disposed within the
access sheath 162. The delivery system 112 is shown extending
distally into the vasculature of the patient's brain adjacent a
vascular defect 160 in the patient's brain.
[0166] Access to a variety of blood vessels of a patient may be
established, including, arteries such as the femoral artery 166,
radial artery 164, and the like in order to achieve percutaneous
access to a vascular defect 160. In general, the patient 158 may be
prepared for surgery and the access artery is exposed via a small
surgical incision 152 and access to the lumen is gained using the
Seldinger technique where an introducing needle is used to place a
wire over which a dilator or series of dilators dilates a vessel
allowing an introducer sheath 162 to be inserted into the vessel.
This would allow the device to be used percutaneously. With an
introducer sheath 162 in place, a guiding catheter 168 is then used
to provide a safe passageway from the entry site to a region near
the target site 154 to be treated. For example, in treating a site
in the human brain, a guiding catheter 168 would be chosen which
would extend from the entry site 152 at the femoral artery up
through the large arteries extending around the heart through the
aortic arch, and downstream through one of the arteries extending
from the upper side of the aorta such as the carotid artery 170.
Typically, a guidewire 159 and neurovascular microcatheter 61 are
then placed through the guiding catheter 168 and advanced through
the patient's vasculature, until a distal end 151 of the
microcatheter 61 is disposed adjacent or within the target vascular
defect 160, such as an aneurysm. Exemplary guidewires 159 for
neurovascular use include the Synchro2.RTM. made by Boston
Scientific and the Glidewire.RTM. Gold Neuro made by MicroVention
Terumo. Typical guidewire sizes may include 0.014 inches and 0.018
inches. Once the distal end 151 of the catheter 61 is positioned at
the site, often by locating its distal end through the use of
radiopaque marker material and fluoroscopy, the catheter is
cleared. For example, if a guidewire 159 has been used to position
the microcatheter 61, it is withdrawn from the catheter 61 and then
the implant delivery apparatus 110 is advanced through the
microcatheter 61.
[0167] Delivery and deployment of device embodiments 10 discussed
herein may be carried out by first compressing the device 10, or
any other suitable device for treatment of a patient's vasculature
discussed herein, to a radially constrained and longitudinally
flexible state as shown in FIG. The device 10 may then be delivered
to a desired treatment site 154 while disposed within the
microcatheter 61, and then ejected or otherwise deployed from a
distal end 151 of the microcatheter 61. In other method
embodiments, the microcatheter 61 may first be navigated to a
desired treatment site 154 over a guidewire 159 or by other
suitable navigation techniques. The distal end of the microcatheter
61 may be positioned such that a distal port of the microcatheter
61 is directed towards or disposed within a vascular defect 160 to
be treated and the guidewire 159 withdrawn. The device 10 secured
to a suitable delivery apparatus 110 may then be radially
constrained, inserted into a proximal portion of the inner lumen
120 of the microcatheter 61 and distally advanced to the vascular
defect 160 through the inner lumen 120.
[0168] Once disposed within the vascular defect 160, the device 10
may then be allowed to assume an expanded relaxed or partially
relaxed state with the permeable shell 40 of the device spanning or
partially spanning a portion of the vascular defect 160 or the
entire vascular defect 160. The device 10 may also be activated by
the application of an energy source to assume an expanded deployed
configuration once ejected from the distal section of the
microcatheter 61 for some embodiments. Once the device 10 is
deployed at a desired treatment site 154, the microcatheter 61 may
then be withdrawn.
[0169] Some embodiments o devices for the treatment of a patient's
vasculature 10 discussed herein may be directed to the treatment of
specific types of defects of a patient's vasculature. For example,
referring to FIG. 18, an aneurysm 160 commonly referred to as a
terminal aneurysm is shown in section. Terminal aneurysms occur
typically at bifurcations in a patient's vasculature where blood
flow, indicated by the arrows 172, from a supply vessel splits into
two or more branch vessels directed away from each other. The main
flow of blood from the supply vessel 174, such as a basilar artery,
sometimes impinges on the vessel where the vessel diverges and
where the aneurysm sack forms. Terminal aneurysms may have a
well-defined neck structure where the profile of the aneurysm 160
narrows adjacent the nominal vessel profile, but other terminal
aneurysm embodiments may have a less defined neck structure or no
neck structure. FIG. 19 illustrates a typical berry type aneurysm
160 in section, where a portion of a wall of a nominal vessel
section weakens and expands into a sack like structure ballooning
away from the nominal vessel surface and profile. Some berry type
aneurysms may have a well-defined neck structure as shown in FIG.
19, but others may have a less defined neck structure or none at
all. FIG. 19 also shows some optional procedures wherein stent 173
or other type of support has been deployed in the parent vessel 174
adjacent the aneurysm. Also, shown is embolic material 176 being
deposited into the aneurysm 160 through a microcatheter 61. Either
or both of the stent 173 and embolic material 176 may be so
deployed either before or after the deployment of a device for
treatment of a patient's vasculature 10.
[0170] Prior to delivery and deployment of a device for treatment
of a patient's vasculature 10, it may be desirable for the treating
physician to choose an appropriately sized device 10 to optimize
the treatment results. Some embodiments of treatment may include
estimating a volume off a vascular site or defect 160 to be treated
and selecting a device 10 with a volume that is substantially the
same volume or slightly over-sized relative to the volume of the
vascular site or defect 160. The volume of the vascular defect 160
to be occluded may be determined using three-dimensional
angiography or other similar imaging techniques along with software
that calculates the volume of a selected region. The amount of
over-sizing may be between about 2% and 15% of the measured volume.
In some embodiments, such as a very irregular shaped aneurysm, it
may be desirable to under-size the volume of the device 10. Small
lobes or "daughter aneurysms" may be excluded from the volume,
defining a truncated volume that may be only partially filled by
the device without affecting the outcome. Such a method embodiment
may also include implanting or deploying the device 10 so that the
vascular defect 160 is substantially filled volumetrically by a
combination of device and blood contained therein. The device 10
may be configured to be sufficiently conformal to adapt to
irregular shaped vascular defects 160 so that at least about 75%,
in some cases about 80%, of the vascular defect volume is occluded
by a combination of device 10 and blood contained therein.
[0171] In particular, for some treatment embodiments, it may be
desirable to choose a device 10 that is properly oversized in a
transverse dimension so as to achieve a desired conformance, radial
force and fit after deployment of the device 10. FIGS. 20-22
illustrate a schematic representation of how a device 10 may be
chosen for a proper fit after deployment that is initially
oversized in a transverse dimension by at least about 10% of the
largest transverse dimension of the vascular defect 160 and
sometimes up to about 100% of the largest transverse dimension. For
some embodiments, the device 10 may be oversized a small amount
(e.g., less than about 1.5 mm) in relation to measured dimensions
for the width, height or neck diameter of the vascular defect
160.
[0172] In FIG. 20, a vascular defect 160 in the form of a cerebral
aneurysm is shown with horizontal arrows 180 and vertical arrows
182 indicating, the approximate largest interior dimensions of the
defect 160. Arrow 180 extending horizontally indicates the largest
transverse dimension of the defect 160. In FIG. 21, a dashed
outline 184 of a device for treatment of the vascular defect 10 is
shown superimposed over the vascular defect 160 of FIG. 20
illustrating how a device 10 that has been chosen to be
approximately 20% oversized in a transverse dimension would look in
its unconstrained, relaxed state. FIG. 22 illustrates how the
device 10 which is indicated by the dashed line 184 of FIG. 21
might conform to the interior surface of the vascular defect 160
after deployment whereby the nominal transverse dimension of the
device 10 in a relaxed unconstrained state has now been slightly
constrained by the inward radial force 185 exerted by the vascular
defect 160 on the device 10. In response, as the filaments 14 of
the device 10 and thus the permeable shell 40 made therefrom have a
constant length, the device 10 has assumed a slightly elongated
shape in the axial or longitudinal axis of the device 10 so as to
elongate and better fill the interior volume of the defect 160 as
indicated by the downward arrow 186 in FIG. 22.
[0173] Once a properly sized device 10 has been selected, the
delivery and deployment process may then proceed. It should also be
noted also that the properties of the device embodiments 10 and
delivery system embodiments 112 discussed herein generally allow
for retraction of a device 10 after initial deployment into a
defect 160, but before detachment of the device 10. Therefore, it
may also be possible and desirable to withdraw or retrieve an
initially deployed device 10 after the fit within the defect 160
has been evaluated in favor of a differently sized device 10. An
example of a terminal aneurysm 160 is shown in FIG. 23 in section.
The tip 151 of a catheter, such as a microcatheter 61 may be
advanced into or adjacent the vascular site or detect 160 (e.g.,
aneurysm) as shown in FIG. 24. For some embodiments, an embolic
coil or other vaso-occlusive device or material 176 (as shown for
example in FIG. 19) may optionally be placed within the aneurysm
160 to provide a framework for receiving the device 10. In
addition, stent 173 may be placed within a parent vessel 174 of
some aneurysms substantially crossing the aneurysm neck prior to or
during delivery of devices for treatment of a patient's vasculature
discussed herein (also as shown for example in FIG. 19). An example
of a suitable microcatheter 61 having an inner lumen diameter of
about 0.020 inches to about 0.022 inches is the Rapid Transit.RTM.
manufactured by Johnson & Johnson. Examples of some suitable
microcatheters 61 may include microcatheters having an inner lumen
diameter of about 0.026 inch to about 0.028 inch, such as the
Rebar.RTM. by Covidien, the Renegade Hi-Flow.RTM. by Boston
Scientific Corporation, and the Mass Transit.TM. by Johnson &
Johnson. Suitable microcatheters having an inner lumen diameter of
about 0.031 inch to about 0.033 inch may include the Marksman.TM.
by Covidien and the Vasco 28.TM. by Balt Extrusion. A suitable
microcatheter 61 having an inner lumen diameter of about 0.039 inch
to about 0.041 inch includes the Vasco 35 by Balt Extrusion. These
microcatheters 61 are listed as exemplary embodiments only, other
suitable microcatheters may also be used with any of the
embodiments discussed herein.
[0174] Detachment of the device 10 from the delivery apparatus 110
may be controlled by a control switch 188 disposed at a proximal
end of the delivery system 112, which may also be coupled to an
energy source 142, which severs the tether 72 that secures the
proximal hub 68 of the device 10 to the delivery apparatus 110.
While disposed within the microcatheter 61 or other suitable
delivery system 112, as shown in FIG. 11, the filaments 14 of the
permeable shell 40 may take on an elongated, non-everted
configuration substantially parallel to each other and a
longitudinal axis of the catheter 61. Once the device 10 is pushed
out of the distal port of the microcatheter 61, or the radial
constraint is otherwise removed, the distal ends 62 of the
filaments 14 may then axially contract towards each other so as to
assume the globular everted configuration within the vascular
defect 160 as shown in FIG. 25.
[0175] The device 10 may be inserted through the microcatheter 61
such that the catheter lumen 120 restrains radial expansion of the
device 10 during delivery. Once the distal tip or deployment port
of the delivery system 112 is positioned in a desirable location
adjacent or within a vascular defect 160, the device 10 may be
deployed out the distal end of the catheter 61 thus allowing the
device to begin to radially expand as shown in FIG. 25. As the
device 10 emerges from the distal end of the delivery system 112,
the device 10 expands to an expanded state within the vascular
defect 160, but may be at least partially constrained by an
interior surface of the vascular defect 160.
[0176] Upon full deployment, radial expansion of the device 10 may
serve to secure the device 10 within the vascular defect 160 and
also deploy the permeable shell 40 across at least a portion of an
opening 190 (e.g., aneurysm neck) so as to at least partially
isolate the vascular defect 160 from flow, pressure or both of the
patient's vasculature adjacent the vascular defect 160 as shown in
FIG. 26. The conformability of the device 10, particularly in the
neck region 190 may provide for improved sealing.
[0177] For some embodiments, once deployed, the permeable shell 40
may substantially slow flow of fluids and impede flow into the
vascular site and thus reduce pressure within the vascular defect
160. For some embodiments, the device, 10 may be implanted
substantially within the vascular defect 160, however, in some
embodiments, a portion of the device 10 may extend into the defect
opening or neck 190 or into branch vessels.
[0178] Once the device 10 has been deployed in the vascular defect,
the isolation of the defect, slowing of flow, reduce pressure or
any combination of these effects may case thrombus formation within
an interior volume of the device 10, outside the device 10 or on
the device itself or some component thereof. In some cases, device
embodiments for treatment of a patient's vasculature 10 may
generally be fabricated by braiding a substantially tubular braided
structure with filamentary elements 14, forming the braided tubular
structure into a desired shape, and heat setting the braided formed
filaments into the desired shape. Once so formed, the ends of the
elongate resilient filaments 14 may then be secured together
relative to each other by any of the methods discussed above and
proximal and distal hubs 66 and 68 added.
[0179] Such a braiding process may be carried out by automated
machine fabrication or may also be performed by hand. An embodiment
of a process for braiding a tubular braided structure by a manual
process is shown in FIG. 27. A plurality of elongate resilient
filaments 14 are secured at one end of an elongate cylindrical
braiding mandrel 202 by a constraining band 204. The band 204 may
include any suitable structure that secured the ends of the
filaments 14 relative to the mandrel 202 such as a band of adhesive
tape, an elastic band, an annular clamp or the like. The loose ends
of the filaments 14 opposite the secured ends are being manipulated
in a braided or woven pattern as indicated by the arrows 206 to
achieve a one over-one under braid pattern for generation of a
braided tubular member 208. As discussed above, although a one
over-one under simple braid pattern is shown and discussed, other
braid or weave patterns may also be used. One such example of
another braid configuration may include a two over-one under
pattern. FIG. 28 illustrates the braided tubular member 208 taking
shape and lengthening as the braiding process continues as
indicated by the arrows 206 in FIG. 28. Once the braided tubular
member 208 achieves sufficient length, it may be removed from the
braiding mandrel 202 and positioned within a shaping fixture such
as the shaping fixture embodiments shown in FIGS. 29 and 30.
[0180] FIG. 29 shows the tubular braided member 208 disposed over
an internal rod mandrel 210 that extends through central lumens of
an internal ball mandrel 212 and a pair of opposed recessed end
forming mandrels 214. The tubular braided member 208 is also
disposed over an outer surface of the internal ball mandrel 212 and
within an inner lumen of each of the end forming mandrels 214. In
order to hold the braided tubular member 208 onto an outer surface
contour of the internal ball mandrel 212, including the recessed
ends 216 thereof, the end forming mandrels 214 are configured to be
pushed against and into the recessed ends 216 of the internal ball
mandrel 212 such that, the inside surface of the braided tubular
member 208 is held against the outer contour of the internal ball
mandiel 212 and fixed in place. This entire fixture 220 with the
inside surface of the braided tubular structure 208 held against
the outside surface of the internal ball mandrel 212 may then be
subjected to an appropriate heat treatment such that the resilient
filaments 14 of the braided tubular member 208 assume or are
otherwise shape-set to the outer contour of the central ball
mandrel 212. In some embodiments, the filamentary elements 14 of
the permeable shell 40 may be held by a fixture configured to hold
the permeable shell 40 in a desired shape and heated to about
475-525 degrees C. for about 5-10 minutes to shape-set the
structure.
[0181] The central ball mandrel 212 may be configured to have any
desired shape so as to produce a shape set tubular braided member
208 that forms a permeable shell 40 having a desired shape and size
such as the globular configuration of the device 10 of FIGS. 3-6
above, or any other suitable configuration. As such, the central
ball mandrel 212 may also be a globular-shaped ball with recesses
in opposing sides for the hubs 66 and 68 that is placed inside the
tubular braid 208. A mold or molds that have one or more pieces
that are assembled to form a cavity with the desired device shape
may also be used in conjunction with or in place of the end forming
mandrels 214. Once the heat set process is complete, fibers,
coatings, and/or surface treatments may be added to certain
filaments, portions of filaments, or all of the permeable shell 40
structure that results. Further, for some embodiments of device
processing, the permeable shell 40 may be formed as discussed above
by securing proximal ends 60 and distal ends 62 of elongate
filamentary elements 14, or to respective proximal and distal hubs
66 and 68.
[0182] FIG. 30 shows another embodiment of a fixture for shape
setting, the permeable shell 40 of a device for treatment of a
patient's vasculature. The fixture embodiment 230 of FIG. 30 may be
used in essentially the same manner as the fixture embodiment 220
of FIG. 29, except that instead of a central ball mandrel 212, an
internal tube mandrel 232 is used in conjunction with an external
tube restraint 234 in order to hold the shape of the braided
tubular member 208 during the heat setting process. More
specifically, the tubular braided member 208 is disposed over an
internal rod mandrel 210 that extends through central lumens of the
internal tube mandrel 232 and pair of opposed recessed end forming
mandrels 214. The tubular braided member 208 is also disposed over
an outer surface of the internal tube mandrel 232 and within an
inner lumen of each of the end forming mandrels 214.
[0183] In order to hold the braided tubular member 208 into a
desired shape, including the recessed ends thereof, the end forming
mandrels 214 are configured to be pushed against and into recessed
ends 238 of the internal tube mandrel 232 such that the inside
surface of the braided tubular member 208 is held against the outer
contour of the internal tube mandrel 232 and fixed in place at the
ends of the tube mandrel 232.
[0184] Between the ends of the tube mandrel 232, the braided
tubular member 208 radially expands outwardly until it touches and
is radially constrained by an inside surface of an external tube
mandrel 234. The combination of axial restraint and securement of
the braided tubular member 208 at the ends of the internal tube
mandrel 232 in conjunction with the inward radial restraint on an
outside surface of the braided tubular member 208 disposed between
the proximal and distal ends thereof, may be configured to produce
a desired globular configuration suitable for the permeable shell
40 of the device 10.
[0185] Once again, this entire fixture 230 with the inside surface
of the ends of the braided tubular structure 208 held against the
outside surface of the ends of the internal tube mandrel 232 and an
outside surface of the braided tubular member 208 radially
constrained by an inside surface 233 of the external tube member
234, may then be subjected to an appropriate heat treatment. The
heat treatment may be configured such that the resilient filaments
14 of the braided tubular member 208 assume or are otherwise
shape-set to the globular contour of the filaments 14 generated by
the fixture 230. In some embodiments, the filamentary elements 14
of the permeable shell 40 may be held by a fixture configured to
hold the braided tubular member 208 in a desired shape and heated
to about 475-525 degrees C. for about 5-10 minutes to shape-set the
structure. The internal tube mandrel 232 and inside surface 233 of
the external tube member 234 may be so configured to have any
desired shape so as to produce a shape set tubular braided member
208 that forms a permeable shell 40 having a desired shape and size
such as the globular configuration of the device of FIGS. 3-6
above, or any other suitable configuration.
[0186] For some embodiments, material may be attached to filaments
14 of the permeable shell 40 of a device 10 such that it
substantially reduces the size of the fenestrations, cells or pores
64 between filaments 14 and thus reduces the porosity in that area.
For example, coating embodiments may be disposed on portions of the
filaments 14 to create small fenestrations or cells and thus higher
density of the permeable shell 40. Active materials such as a
responsive hydrogel may be attached or otherwise incorporated into
permeable shell 40 of some embodiments such that it swells upon
contact with liquids over time to reduce the porosity of the
permeable shell 40.
[0187] Device embodiment 10 and any other suitable device
embodiment discussed herein may be coated with various polymers to
enhance its performance, fixation and/or biocompatibility. In
addition, device embodiments 10 may be made of various biomaterials
known in the art of implant devices including but not limited to
polymers, metals, biological materials and composites thereof.
Device embodiments discussed herein may include cells and/or other
biologic material to promote healing. Device embodiments discussed
herein may also be constructed to provide the elution or delivery
of one or more beneficial drugs, other bioactive substances or both
into the blood or the surrounding tissue.
[0188] In some cases, permeable shell embodiments 40 of devices for
treatment of a patient's vasculature 10 may include multiple
layers. A first or outer layer may be constructed from a material
with low bioactivity and hemocompatibility so as to minimize
platelet aggregation or attachment and thus the propensity to form
clot and thrombus. Optionally, an outer layer may be coated or
incorporate an antithrombogenic agent such as heparin or other
antithrombogenic agents described herein or known in the art. One
or more inner layers disposed towards the vascular defect in a
deployed state relative to the first layer may be constructed of
materials that have greater bioactivity and/or promote clotting and
thus enhance the formation of an occlusive mass of clot and device
within the vascular defect. Some materials that have been shown to
have bioactivity and/or promote clotting include silk, polylactic
acid (PLA), polyglycolic acid (PGA), collagen, alginate, fibrin,
fibrinogen, fibronectin, Methylcellulose, gelatin, Small Intestinal
Submucosa (SIS), poly-N-acetylglucosamine and copolymers or
composites thereof.
[0189] Bioactive agents suitable for use in the embodiments
discussed herein may include those having a specific action within
the body as well as those having nonspecific actions. Specific
action agents are typically proteinaceous, including thronthogenic
types and/or forms of collagen, thrombin and fibrogen (each of
which may provide an optimal combination of activity and cost), as
well as elastin and von Willebrand factor (which may tend to be
less active and/or expensive agents), and active portions and
domains of each of these agents. Thrombogenic proteins typically
act by means of a specific interaction with either platelets or
enzymes that participate in a cascade of events leading eventually
to dot formation. Agents having nonspecific thrombogenic action are
generally positively charged molecules, e.g., polymeric molecules
such as chitosan, polylysine, poly(ethylenimine) or acrylics
polymerized from acrylimide or methacrylamide which incorporate
positively-charged groups in the form of primary, secondary, or
tertiary amines or quaternary salts, or non-polymeric agents such
as (tridodecylmethylammonium chloride). Positively charged
hemostatic agents promote clot formation by a non-specific
mechanism, which includes the physical adsorption of platelets via
ionic interactions between the negative charges on the surfaces of
the platelets and the positive charges of the agents
themselves.
[0190] Device embodiment 10 and any other suitable device
embodiment discussed herein may include a surface treatment or
coating on a portion, side or all surfaces that promotes or
inhibits thrombosis, dotting, healing or other embolization
performance measure. The surface treatment or coating may be a
synthetic, biologic or combination thereof. For some embodiments,
at least a portion of an inner surface of the permeable shell 40
may have a surface treatment or coating made of a biodegradable or
bioresorbable material such as a polylactide, polyglycolide or a
copolymer thereof. Another surface treatment or coating material
that may enhance the embolization performance of a device includes
a polysaccharide such as an alginate based material. Some coating
embodiments may include extracellular matrix proteins such as ECM
proteins. One example of such a coating may be Finale.TM.
Prohealing coating which is commercially available from Surmodics
Inc., Eden Prairie, Minn. Another exemplary coating may be
Polyzene-F, which is commercially available from CeloNovo
BioSciences, Inc., Newnan, Ga. In some embodiments, the coatings
may be applied with a thickness that is less than about 25% of a
transverse dimension of the filaments 14.
[0191] Antiplatelet agents may include aspirin, glycoprotein
IIb/IIIa receptor inhibitors (including, abcixiinab, eptifibatide,
tirofiban, lamifiban, fradafiban, cromafiban, toxifiban, XV454,
lefradafiban, klerval, lotrafiban, orbofiban, and xemilofiban),
dipyridanlole, apo-dipyridamole, persantine, prostacyclin,
ticlopidine, clopidogrel, cromafiban, cilostazol, and nitric oxide.
To deliver nitric oxide, device embodiments may include a polymer
that releases nitric oxide. Device embodiments 10 may also deliver
or include an anticoagulant such as heparin, low molecular weight
heparin, hirudin, warfarin, bivalirudin, hirudin, argatroban,
forskolin, ximelagatran, vapiprost, prostacyclin, and prostacyclin
analogues, dextran, synthetic antithrombin, Vasoflux, argatroban,
efegatran, tick anticoagulant peptide, Ppack, HMG-CoA reductase
inhibitors, and thromboxane A2 receptor inhibitors.
[0192] In some embodiments, the permeable shell 40 of a device 10
may be coated with a composition that may include nanoscale
structured materials or precursors thereof (e.g., self-assembling
peptides). The peptides may have with alternating hydrophilic and
hydrophobic monomers that allow them to self-assemble under
physiological conditions. The composition may comprise a sequence
of amino acid residues. In some embodiments, the permeable shell
may include a thin metallic film material. The thin film metal may
be fabricated by sputter deposition and may be formed in multiple
layers. The thin film may be a nickel-titanium alloy also known as
nitinol.
[0193] In some instances, saccular aneurysms may have a generally
circular flow dynamic of blood as indicated by arrows 250 shown in
FIG. 31. While the shell of a single layer device, such as device
10, slows flow into the aneurysm, thrombosis and embolization may
be further enhanced by an internal porous structure. In particular,
a structure that is formed so that the circular flow 250, and in
particular the highest velocity region is forced to pass through
one or more porous layers may have a synergistic treatment effect
and promote rapid thrombosis.
[0194] As discussed above with regard to the deployment method
embodiment shown in FIGS. 23-26, once a properly sized device for
treatment of a patient's vasculature 10 has been selected, the
delivery and deployment process may take place. During deployment,
the tip of a microcatheter 61 may be advanced into or adjacent the
vascular site or defect 160. The device for treatment of a
patient's vasculature 10 may be inserted through the microcatheter
61 such that the catheter lumen restrains radial expansion of the
device during delivery. Once the distal tip or deployment port of
the delivery system is positioned in a desirable location adjacent
or within a vascular defect 160, the device 10 may be deployed out
the distal end of the catheter thus allowing the device to begin to
radially expand as shown in FIG. 25. As the device emerges from the
distal end of the delivery system, the device 10 expands radially
outward to an expanded state within an interior volume the vascular
defect. Upon deployment, the device 10 may also be at least
partially constrained by an interior surface of the vascular defect
160 depending on the sizing of the device relative to the size of
the interior surface of the vascular defect 160. Upon full
deployment, radial expansion of the device 10 may serve to exert an
outward radial force of the outside surface of the device against
the inside surface of the vascular defect to mechanically secure
the device within the vascular defect. Deployment of the device 10
may serve to partially isolate the vascular defect from flow,
pressure or both coming from the patient's vasculature adjacent the
vascular defect.
[0195] In any of the device embodiments discussed or incorporated
herein for treatment of a patient's vascular defect or aneurysm,
the device may comprise one or more composite filaments. A
composite filament (e.g., wires) may be defined as a filament that
comprises a plurality of materials in either a mixture or alloy or
in a composite structure where two materials are physically
combined into one. The addition of at least some composite wires
into the device may provide improved visibility of the device under
external imaging such as x-ray, fluoroscopy, magnetic resonance
imaging and the like. In some embodiments, composite wires may
provide improved mechanical characteristics.
[0196] For some composite filament embodiments, the composite
filaments may be disposed in a coaxial arrangement with one
material substantially inside the other as shown. In FIG. 32. One
known method of fabrication of such a coaxial composite wire is a
drawn filled tube wire wherein the materials of the drawn filled
tube are combined but retain their individual mechanical
properties. Drawn filled tube wires are commercially available from
Ft. Wayne Metals, Ft. Wayne, Ind. In some cases, the process for
producing drawn filled tube filaments may include extreme
compressive forces such that the mechanical bond between an outer
surface 334 of the internal fill wire 332, and an internal surface
338 of the external tube 336 is metallurgically sound. In some
instances, a plurality of external tubes, each of a different
material, may be layered over the internal wire and each other in
order to combine the mechanical properties of the plurality of
materials. For such embodiments, the drawn filled tube filament may
include 2, 3, 4, 5 or more external tube levers. In some
embodiments, the drawn filled tube wires are formed of a
combination of an external nitinol (NITi) tube and a highly
radiopaque fill wire that may be concentrically disposed within the
external tube. Various radiopaque materials and metals known in the
art may be used as the fill wire including but not limited to gold,
platinum, tantalum and the like. One advantage of a composite with
a NiTi exterior and internal highly radiopaque fill wire is that
the device can substantially maintain its highly elastic or
superelastic behavior and the majority of the blood contacting
surfaces remain nitinol. This allows for a device with
substantially improved visibility under x-ray imaging while
maintaining the proper range of mechanical characteristics.
[0197] In some cases, the specific construction of a drawn filled
tube wire or filament may be important in order to maintain desired
performance characteristics of a device for treatment of a vascular
defect. More specifically, it may be important to balance the
stiffness, elasticity and radiopacity of the composition. In
particular, for drawn filled tube filament embodiments that include
an internal wire 332 of ductile radipaque material such as platinum
and an outer tube 336 of an elastic or superelastic material such
as NiTi, it can be necessary to carefully balance the ratio of the
percent cross sectional area of the internal wire with regard to
the overall cross sectional area of the filament. Such a ratio may
be referred to as a fill ratio. If an embodiment includes too
little radiopaque or highly radiopaque internal tube material
relative to the external tube material, there may not be sufficient
radiopacity and visibility. On the other hand, if an embodiment
includes too much internal wire material with respect to the
elastic external tube, the mechanical properties of the ductile
radiopaque material may overwhelm the elastic properties of the
outer tube material and the filaments may be prone to taking a set
after compression etc. resulting in permanent deformation. For some
embodiments, a desired composite or drawn filled tube wire may be
constructed with a fill ratio of cross sectionai area of internal
fill wire to cross sectional area of the entire composite filament
of between about 10% and about 50%, more specifically between about
20% and about 40%, and even more specifically, between about 25%
and about 35%.
[0198] In some embodiments, the number of composite wires may be
between about 40 and 190, and between about 50 and 190 in other
embodiments, and between about 70 and 150 in other embodiments. In
some embodiments, the devices for treatment of a patient's
vasculature may have at least about 25% composite wires relative to
the total number of wires and in some embodiments such devices may
have at least about 40% composite wires relative to a total number
of wires in the device. For example, a first subset of elongate
resilient filaments may comprise filaments, each having a composite
of highly radiopaque material and a high strength material, and a
second subset of elongate resilient filaments may consist
essentially of a high strength material. For example, the highly
radiopaque material may comprise platinum, platinum alloy such as
90% platinum/10% iridium, or gold or tantalum. The high strength
material may comprise NiTi. While composite wires may provide
enhanced visualization and/or mechanical characteristics, they may
in some configurations have reduced tensile strength in comparison
to NiTi wires of a similar diameter. In other configurations,
depending on their diameter, the composite wires may increase the
collapsed profile of the devices. Therefore, it may be beneficial
to minimize the number. Lower percentages of composite wires may
not be sufficiently visible with current imaging equipment
particularly in neurovascular applications where the imaging is
done through the skull. In addition, too many composite wires (or
composite wires with extremely high fill ratios) may result in
devices with excessive artifact on CT or MRI imaging. The described
ratios and amounts of highly radiopaque material provide a unique
situation for neurovascular implants where the periphery of the
device is just visible under transcranial fluoroscopy but the
device imaged area is not completely obliterated (i.e., due to
artifact) as it is with conventional embolic coils that are made
substantially out of platinum or platinum alloys.
[0199] One manner of achieving the desired degree of radiopacity is
by selecting a particular combination of fill ratio of the
composite wires and the percent of composite wires in relation to
the total number of wires. Devices according to embodiments having
a single layer braided (woven) structure were constructed. For
example, an embodiment of a braided structure comprising 72
composite Platinum/NiTi drawn filled tube wires having a 0.00075''
diameter and a platinum fill ratio of 30% and 72 NiTi wires having
a 0.00075'' diameter was constructed. The total percent of platinum
(by total cross sectional area) in the braided structure was about
15%. Another embodiment of a braided structure comprising 108
composite Platinum/NiTi drawn filled tube wires having a 0.001''
diameter and a platinum fill ratio of 30% and 72 NiTi wires having
a 0.00075'' diameter was constructed. The total percent of platinum
in the braided structure was about 22%. Still another embodiment of
a braided structure comprising 72 composite Platinum/NiTi drawn
filled tube wires having a 0.00125'' diameter and a platinum fill
ratio of 30% and 108 NiTi wires having a 0.00075'' diameter was
constructed. The total percent of platinum in the braided structure
was about 19.5%. Yet another embodiment of a braided structure
comprising 108 composite Platinum/NiTi drawn filled tube wires
having a 0.00125'' diameter and a platinum fill ratio of 30% and
108 NiTi wires having a 0.00075'' diameter was constructed. The
total percent of platinum in the braided structure was about 22%.
Devices constructed according to each of these embodiments were
each implanted into living bodies and imaged using fluoroscopy. In
each case, the periphery of the device was visible under
transcranial fluoroscopy but the device imaged area was not
completely obliterated (i.e., due to artifact).
[0200] In some embodiments the total cross sectional area of the
highly radiopaque material is between about 11% and about 30% of
the total cross sectional area of the plurality of elongate
elements. In some embodiments the total cross sectional area of the
highly radiopaque material is between about 15% and about 30% of
the total cross sectional area of the plurality of elongate
elements. In some embodiments the total cross sectional area of the
highly radiopaque material is between about 15% and about 22% of
the total cross sectional area of the plurality of elongate
elements. In some embodiments the total cross sectional area of the
highlyradiopaque material is between about 19% and about 30% of the
total cross sectional area of the plurality of elongate elements.
In some embodiments the total cross sectional area of the highly
radiopaque material is between about 11% and about 18.5% of the
total cross sectional area of the plurality of elongate
elements.
[0201] Because the radiopacity of the composite filaments
comprising a highly radiopaque material can allow sufficient device
visualization (e.g., on fluoroscopy), it may be desired to make one
or more of the hubs from less radiopaque or non-radiopaque
materials. In some embodiments, platinum, platinum alloy (e.g., 90%
Platinum/10% Iridium), may not be desired, if their radiopacity
would overpower the radiopacity of the composite filaments, and
thus, make their delineation difficult. The use of less radiopaque
or non-radiopaque materials to make the hubs may thus be desired in
these embodiments, but can also be used on the hubs of other
embodiments. One or more titanium or titanium alloy hubs or NiTi
hubs may be used in place of highly radiopaque hubs. The use of
titanium, titanium ahoy, or NiTi hubs may also aid in welding to
NiTi filaments, as their melt temperatures are more closely matched
than if, for example, platinum, platinum alloy, or gold hubs were
being used. The result can be a joint between the filaments and the
hub that has a higher tensile breakage force. Joints of this
variety were constructed and demonstrated an approximately 48%
improvement in tensile force.
[0202] FIG. 33 illustrates an embodiment of a combination mesh and
coil device 1700 for treatment of a vascular defect. The
combination mesh and coil device 1700 comprises a mesh portion 1702
and a coil portion 1704. The mesh portion 1702 has a proximal end
1708 and a distal end 1710, and may incorporate any number of the
embodiments described herein, but is generally braided from
filaments 1712. The filaments 1712 may be secured at the proximal
end 1708 with a marker band 1715. The coil portion 1704 comprises a
proximal end 1719 and a distal end 1721, and may be constructed
from a primary platinum or platinum alloy coil (for example, 92%
Platinum, 8% Tungsten), wound into one of more secondary diameters.
The coil portion 1704 may be wound from single-filar or multi-filar
wire 1723 having a diameter of between 0.0008 inches and 0.005
inches, or between 0.001 inches and 0.0035 inches. The secondary
diameter 1725 may approximate the diameter 1621 of the mesh portion
1702, or may be less than the diameter 1621 of the mesh portion
1702, depending on the application. For example, it may be
configured to be about one-half of the diameter 1621 of the mesh
portion 1702. The distal end 1721 may include one or more first
loops 1717 having a reduced secondary diameter 1727. The coil
portion 1704 may be secured to the mesh portion 1702 at a band
1729, which may or may not need to be radiopaque, because of the
general radiopacity of the platinum material of the coil portion
1704. The combination mesh and coil device 1700 is configured to
have a relaxed, expanded state, as shown in FIG. 33, wherein the
mesh portion 1702 is a globular or other shape, and the coil
portion 1704 has its one or more secondary diameters 1725, 1727,
The combination mesh and coil device 1700 also has a radially
constrained, elongated state for delivery through a microcatheter,
wherein the mesh portion 1702 is collapsed and elongated, and the
coil portion 1704, is straightened and elongated.
[0203] The potential utility of the coil portion 1704 is multifold.
First, the coil portion 1704, being the initial portion of the
combination mesh and coil device 1700 that is delivered to the
vascular defect, can atraumatically track around the diameter of
the vascular defect, and aid the engagement of the combination mesh
and coil device 1700 within the vascular defect. The secondary
diameter 1725 of one or more loops 1714 may be chosen to
approximate the diameter 1621 of the mesh portion 1702, or in some
cases be slightly larger, so that the coil portion 1704 may form a
three-dimensional frame around the vascular defect, with the mesh
portion 1702 being expanded within this three-dimensional frame.
The reduced secondary diameter 1727 may be chosen to be 50% to 85%
of the secondary diameter 1725, and serves to keep the coil portion
1704 within the vascular defect, and out of, for example, the
parent vessel, as the coil portion 1704 is first being inserted
within the vascular defect. An additional use of the coil portion
1704 is to serve as a biasing member for pushing the expanded mesh
portion 1702 against the opening of the vascular defect (such as
the neck of an aneurysm). This can allow a smaller diameter mesh
portion 1702 to effectively disrupt flow inside a larger diameter
vascular defect, without having to volumetrically fill the entire
vascular defect. These uses will be illustrated in more detail in
the following figures.
[0204] FIGS. 34A-34B illustrate a method for implanting a
combination mesh and coil device 1700b through a microcatheter 1761
into an aneurysm 160 having a neck 167 and a dome 161. The
combination mesh and coil device 1700b comprises a mesh portion
1702b and a coil portion 1704b. In FIG. 34A, the coil portion 1704a
is delivered out of the microcatheter 1761. The coil portion 1704b
has helical shape and has a significant spring constant in the
axial direction. The length of the helix (i.e., number of coils) is
chosen, so that the coil portion 1704b will be able to be axially
compressed between the dome 161 of the aneurysm 160 and the mesh
portion 1702b when the mesh portion 1702b is delivered completely
out of the microcatheter 1761 and self-expands in a portion
adjacent the neck 167 of the aneurysm 160 (FIG. 34B). After the
delivery of the entire combination mesh and coil device 1700b into
the aneurysm 160, the combination mesh and coil device 1700b is
detached from its delivery apparatus 1732b and the microcatheter
1761 is retracted and removed from the patient. The delivery
apparatus 1732b may be removed completely from the microcatheter
1761, before the microcatheter 1761 is retracted and removed from
the patient, or may be only retracted within the microcatheter
1761. The mesh portion 1702b may incorporate at least some
radiopaque filaments, for example made from platinum or platinum
alloy. The compressed coil portion 1704b places a force F onto the
expanded mesh portion 1702b which holds it against the neck 167 of
the aneurysm 160. A force (axial bias) of as high of 0.27 grains or
higher has been predicted to be exerted from flow momentum on a
basilar tip aneurysm neck during a portion of each cardiac cycle.
The spring constant of the coil portion 1704b can be configured so
that when at least partially compressed, a force F (axial bias) of
greater than 0.27 grams is applied on the mesh portion 1702b and
thus against the neck 167 of the aneurysm. The basilar tip aneurysm
typically has the highest flow of cerebral aneurysms. Calculating
the effect that systolic and diastolic blood pressure have on the
expansion and contraction and of a blood vessel and aneurysm at the
neck and the area surrounding the neck, some assumptions can be
made to further expand the requirements of the force F. Choosing a
low diastolic pressure of 40 mm Hg and a neck diameter of 2.5 mm, a
force of 2.67 grams is predicted. Choosing a high diastolic
pressure of 120 mm Hg and a neck diameter of 3.6 mm, a force of
16.6 grams is predicted. Therefore, the coil portion 1704b may be
configured so that when at least partially compressed, a force F of
greater than 0.27 grams, or more particularly a force F greater
than 2.67 grams, and more particularly a force F greater than 16.6
grams is applied on the mesh portion 1702b and thus against the
neck 167 of the aneurysm. Because the mesh portion 1702b does not
need to fill the entire volume of the aneurysm 160, the mesh
portion 1702b may be significantly smaller, and by being smaller,
may fit into smaller microcatheter lumens and be deliverable
through more tortuous blood vessels, and thus be usable in more
remotely located aneurysms. The combination mesh and coil device
1700b is thus usable in large or giant aneurysms, but still
deliverable with standard, small diameter microcatheter lumens.
[0205] FIGS. 35A-35B illustrate a method for implanting a
combination mesh and coil device 1700c, through a microcatheter
1761 into an aneurysm 160 having a neck 167 and a dome 161. The
combination mesh and coil device 1700c comprises a mesh portion
1702c and a coil portion 1704c. In FIG. 35A, the coil portion 1704c
is delivered out of the microcatheter 1761. The coil portion 1704c
has helical shape and has one or more loops. The purpose of the
coil portion 1704c is to protect the aneurysm 160 while the
combination mesh and coil device 1700c is delivered from the
microcatheter 1761 and positioned into the aneurysm 160 before and
after the mesh portion 1702c self-expands within the aneurysm 160
(FIG. 35B). After the delivery of the entire combination mesh and
coil device 1700c into the aneurysm 160, the combination mesh and
coil device 1700c is detached from its delivery apparatus 1732c and
the microcatheter 1761 is retracted and removed from the patient.
The mesh portion 1702c may incorporate at least some radiopaque
filaments, for example made from platinum or platinum alloy. The
combination mesh and coil devices 1700a, 1700b, 1700c may also each
share one or more characteristics of each other (i.e., shape, force
application, atraumatic coil).
[0206] FIGS. 35C-35D illustrate an embodiment of a mesh device 2200
that has been delivered through a microcatheter 1761. The mesh
device 2200 includes a mesh portion 1702 comprising filaments 2212
that are secured at a distal end 2213 at a cylindrical hub 2215.
The filaments 2212, each having a filament end 2221, extend beyond
a distal end 2217 of the cylindrical hub 2215 in a generally radial
direction, forming a circular projection 2219 having diameter D.
FIGS. 35E-3F illustrate the mesh device 2200 being delivered from
the microcatheter 1761 (e.g, into a vascular defect). In some
embodiments, the circular projection 2219 is analogous to the coil
portion 1704b of the combination mesh and coil device 1700b of
FIGS. 34A-34B, and may be configured to apply a biasing force. In
some embodiments, the filaments 2212 are braided. In some
embodiments, the circular projection 2219 is configured to protect
an aneurysm 160, in a manner similar to the coil portion 1704c of
the combination mesh and coil device 1700c of FIGS. 35A-35B. The
circular projection 2219 may include filaments 2212 that are
braided, partially braided, or have the braid undone or
unraveled.
[0207] FIG. 36 illustrates an embodiment of a mesh device 2050
having a single tubular mesh structure 2052 secured at its proximal
end 2054 at a proximal hub 2056, and secured at its distal end 2058
at a distal hub 2060. The inner length IL of the mesh device 2050
is relatively short in comparison to the overall length L.sub.O,
because of the shape that is heat set into the single tubular mesh
structure 2052, the shape comprising a concavity 2062.
[0208] FIG. 37 illustrates an embodiment of a multi-lobe mesh
device 2100 having a center lobe 2102 secured at its proximal end
2104 at a proximal hub 2106, and secured at its distal end 2108 at
a center hub 2110, in a similar manner as the single tubular mesh
structure 2052 or the mesh device 2050 of FIG. 36. However, the
multi-lobe mesh device 2100 further comprises a distal lobe 2112
that is able to nest within a concavity 2114 within the center lobe
2102. The distal lobe 2112 is secured by the center hub 2110 and a
distal hub 2116. Additionally, multi-lobe mesh device 2100
comprises a proximal lobe 2118, secured by the proximal hub 2106.
In some embodiments, the entire multi-lobe mesh device 2100 is
configured to be implanted within a vascular defect. In some
embodiments the center lobe 2102 and the distal lobe 2112 are
configured to reside in the vascular defect while the proximal lobe
2118 is configured to reside on the other side of the entry point
to the vascular defect. For example, in FIG. 40, the proximal lobe
2118 resides at least partially in the parent artery 414 adjacent
the neck 167 of the aneurysm (vascular defect 160). In some
embodiments, the center lobe 2102 and the proximal lobe 2118 serve
as bookends to hold the multi-lobe mesh device 2100 at the neck
167.
[0209] Turning to FIG. 38, the multi-lobe mesh device 2100 is shown
in a radially constrained state for delivery along a longitudinal
axis 2128 through a microcatheter 61. The multi-lobe mesh device
2100 is releasably coupled to a delivery apparatus 2122 at its
proximal end 2124. The distal end 2120 of the multi-lobe device
2100 in its radially constrained state corresponds to a distal
extremity of the distal lobe 2112. The serial array 2126 of the
three lobes 2112, 2102, 2118 assures that upon delivery, there are
no layer overlaps that would increase profile. The multi-lobe mesh
device 2100 thus has a small radially constrained profile, and may
be deliverable through microcatheter 61 having an inner diameter as
small as 0.021'' and even as small as 0.017''.
[0210] FIG. 39 illustrates a multi-lumen mesh device 2130 having a
proximal lobe 2134 and a distal lobe 2132, the proximal lobe 2134
secured at a proximal hub 2136 and the distal lobe 2132 secured at
the proximal hub 2136 and a center hub 2138. As in the embodiment
of the multi-lobe mesh device 2100 of FIG. 40, the proximal lobe
2134 may be configured to reside within the vascular defect or to
reside within the parent artery, and thus straddling the neck.
[0211] Turning to FIGS. 41 and 42, a castellated mandrel assembly
1038 is illustrated and comprises a castellated mandrel 1034 having
a radiused cap 1044 within its central cavity 1046. The castellated
mandrel 1034 includes a cylindrical battlement-like structure 1048
having a plurality of slots, or crenels 1052, separated by a
plurality of posts, or merlons 1054. The embodiment illustrated in
FIGS. 41 and 42 comprises 18 crenels 1052 and 18 merlons 1054,
however, alternative embodiments may include 27 crenels 1052 and 27
merlons 1054, or other quantities. The radiused cap 1044 has a
convex radius 1056 whose surface 1058 is preferably contained
within the portion of the central cavity 1046 surrounded by the
battlement-like structure 1048. A pin 1064 extends from the
radiused cap 1044, and extends into a hole 1066 within the
castellated mandrel 1034. The radiused cap 1044 may be secured to
the castellated mandrel 1034 by attaching the pin 1064 to the hole
1066 using a threaded screw, adhesive, epoxy, welding, or analogous
methods. The radiused cap 1044 and the castellated mandrel 1034 may
be made from rigid, durable materials, such as stainless steel.
[0212] The loading of a castellated mandrel assembly 1038 for the
process of constructing an embodiment of a mesh device is
illustrated in FIGS. 43A-43C. Merlons 1054a-r are circumferentially
arrayed around the battlement-like structure 1048, with crenels
1052a-r between each of the merlons 1054a-r. In FIG. 43A, a first
filament 1412a is loaded in a downward direction into crenel 1052a
(between merlons 1054r and 1054a) and crenel 1052j (between merlons
1054i and 1054j) and secured to the castellated mandrel assembly
1038. The first filament 1412a may be secured, for example, so that
a central portion 1068a of the first filament 1412a is held snugly
across the surface 1058 of the convex radius 1056 of the radiused
cap 1044. In an 18-crenel embodiment of the castellated mandrel
assembly 1038, the locations of crenel 1052a and 1052j are
180.degree. from each other, approximating, for example, 12 o'clock
and 6 o'clock locations on a clock face. However, other,
non-180.degree. configurations, such as the configuration of FIG.
43D, may be chosen for the filament 1412a, or subsequent filaments
1412 to be loaded. In FIG. 43B, a second filament 1412b is loaded
in a downward direction into crenel 1052b (between merlons 1054a
and 1054b) and crenel 1052k (between merlons 1054j and 1054k) and
secured to the castellated mandrel assembly 1038. A central portion
1068b of the filament 1412b is crossed over the central portion
1068a of the first filament 1412a, and held snugly across the
convex radius 1056 of the radiused cap 1044. This loading is
continued until ail filaments 1412 are loaded and secured to the
castellated mandrel assembly 1038. Multiple filaments 1412 may be
loaded into each of the crenels 1052, or only certain selected
crenels 1052. After loading all of the filaments 1412 into the
crenels 1052 and securing the filaments 1412 to the castellated
mandrel assembly 1038, the filaments 1412 are ordered and extended
radially, and the braiding process is performed as previously
described in relation to these figures. The resulting mesh device,
such as the mesh device 1800 of FIG. 47, has substantially closed
distal apex 1807, because of the manner in which the filaments 1412
are layered over each other at the radiused cap 1044. The mesh
device 1800 of FIG. 47 may be made with, for example, 72 to 216
filaments 1412, but because the loading of the mandrel produces the
equivalent of two filaments 1412 from a single piece of wire, there
are only 36 to 108 pieces of wire required. A mixture of platinum
or platinum alloy filaments with Nickel-Titanium filaments may be
chosen to add radiopacity to the mesh device 1800, especially at
the distal end. Alternatively, drawn filled tubes (DFT) having a
radiopaque (e.g., platinum or platinum alloy) core may be used. In
the mesh device 1800 of FIG. 47, filament diameters may range from
about 0.0005 inches to about 0.002 inches, or from about 0.00075
inches to 0.00125 inches
[0213] FIG. 43C illustrates a top view of the loaded castellated
mandrel assembly 1038 of the mesh device 1800, made in conjunction
with the method described in FIGS. 43A-43B. Because each of the
filaments 1412 crosses a center crossing point 1073, the
substantially closed distal apex 1807 of the mesh device 1800
includes many layers of filaments 1412 at this center crossing
point 1073. However, shaping and heat forming of the mesh device
1400 can at least partially reform some or all of the filaments
1412 at the center crossing point 1073, spreading them out in order
to lessen the bulk at the center crossing point.
[0214] An alternative filament loading method is illustrated in
FIG. 43D. Filaments 1115 are loaded in a staggered manner. Filament
1115a is loaded into crenels 1052a and 1052f; thus, it extends
inside merlons 1054a, 1054b, 1054c, 1054d, and 1054e, and is held
snugly across a portion of the convex radius 1056 of the radiused
cap 1044. Filament 1115b is loaded into crenels 1052b and 1052g,
and thus it extends inside merlons 1054b, 1054c, 1054d, 1054e, and
1054f, and crosses on top of filament 1115a. This is continued
until all of the filaments 1115 are loaded, and the configuration
of FIG. 43D is visible. In this embodiment, a central opening 1091
is formed, in contrast to the closed distal apex 1807 of the mesh
device 1800. The size of the central opening 1091 can be varied,
depending on both the diameter of the castellated mandrel 1034 at
the battlement-like structure 1048, and the total number of crenels
1052 skipped when loading each filament 1115.
[0215] The forming of a mesh device having an open distal end is
illustrated in FIGS. 44A-44B. FIG. 44A, a first filament 1512a is
loaded in a downward direction into crenel 1052a (between merlons
1054r and 1054a) and crenel 1052b (between merlons 1054a and
1054b). A central portion 1168a of the first filament 1512a is held
snugly around the merlon 1054a and a first portion 1170a and a
second portion 1172a of the filament 1512a are secured to the
castellated mandrel assembly 1038. In FIG. 44B, a second filament
1512b is loaded in a downward direction into crenel 1052b (between
merlons 1054a and 1054b) and crenel 1052c (between merlons 1054b
and 1054c). A central portion 1168b of the second filament 1512b is
held snugly around the merlon 1054b and a first portion 1170b and a
second portion 1172b are secured to the castellated mandrel
assembly 1038. This loading is continued until all the filaments
1512 are loaded and secured to the castellated mandrel assembly
1038. Multiple filaments 1512 may be loaded around each of the
merlons 1054, or only certain selected merlons 1054. After loading
all of the filaments 1512 into the crenels 1052 and securing the
filaments 1512 to the castellated mandrel assembly 1038, the
filaments 1512 are ordered and extended radially, and the braiding
process is performed as previously described in relation to these
figures. A plurality of loops results from the central portions
1168 of the filaments 1512 that are initially curved around the
merlons 1054 of the castellated mandrel assembly 1038. The diameter
of the castellated mandrel 1034 at the battlement-like structure
1048 may be varied, in order to control the diameter of the open
portion 1518. The number and size of the merlons 1054 may be varied
in order to control the number and size of the loops 1516. The
loops 1516 may serve as a blunt leading portion as the mesh device
1500 is expanded within a vascular defect, increasing the safety of
its use.
[0216] FIG. 45 illustrates an embodiment of a multi-lobe mesh
device 1800 for treatment of a patient's vasculature. In this
particular embodiment, the multi lobe mesh device 1800 comprises a
proximal lobe 1802, a center lobe 1804, and a distal lobe 1806. In
some embodiments, each of the lobes 1802, 1804, 1806 is formed from
a single layer braided tubular member. The lobes may be
individually braided, and connected together in parallel via a
proximal hub 1808, a central hub 1810, and a distal hub 1812. In
some embodiments, the proximal lobe 1802 may be configured to have
a first porosity P.sub.1, which is relatively small and configured
to be placed at an entry portion or neck portion of a vascular
defect, and to promote occlusion of the vascular defect. In some
embodiments, the center lobe 1804 may be configured to have a
radial stiffness, and overall mechanical characteristics that are
configured to support the multi-lobe mesh device 1800 within the
vascular defect. In some embodiments, the center lobe 1804 may have
a second porosity P.sub.2, which is greater than the first porosity
P.sub.1. In some embodiments, the distal lobe 1806 may be
configured to have a third porosity P.sub.3, which is relatively
small and configured to be placed at a distal portion or a dome
portion of a vascular defect. In some embodiments, the distal lobe
1806 having the third porosity P.sub.3 may be configured to be
placed adjacent a prior rupture site, and may be configured to
provide a protective fine mesh to limit or eliminate re-rupture. In
some embodiments, the first porosity P.sub.1 of the proximal lobe
1802 may be approximately equal to the third porosity P.sub.3 of
the distal lobe 1806. In some embodiments, the distal lobe 1806
[0217] In some embodiments the proximal lobe 1802 may be
constructed from between about 108 and about 180 filaments 1814. In
some embodiments, the proximal lobe 1802 may be constructed from
between about 54 and about 90 nitinol filaments and between about
54 and about 90 drawn filled tube (DFT) filaments. In some
embodiments, the DFT filaments may comprise an outer, high-strength
material such as nitinol, and an inner core of a highly radiopaque
material, such as platinum, platinum alloy such as 90% platinum/10%
iridium, or gold or tantalum. In some embodiments, the DFT
filaments may comprises a cross-sectional fill area ratio of
between about 10% and about 50% of the highly radiopaque material.
In some embodiments, the DFT filaments may comprises a
cross-sectional fill area ratio of between about 20% and about 40%
of the highly radiopaque material. In some embodiments, the DFT
filaments may comprises a cross-sectional fill area ratio of
between about 25% and about 35% of the highly radiopaque material.
In some embodiments, the proximal lobe 1802 may comprises nitinol
filaments having a transverse dimension or diameter of between
about 0.0004'' and about 0.0006'', and DFT filaments having a
transverse dimension of between about 0.0006'' and about 0.0009''.
In some embodiments, the proximal lobe 1802 may comprise about 72
nitinol filaments having a transverse dimension of about 0.0005 and
about 72 DFT filaments having a transverse dimension of about
0.00075''.
[0218] In some embodiments the center lobe 1804 may be constructed
from between about 36 and about 54 filaments 1816. In some
embodiments, the center lobe 1804 may be constructed from DFT
filaments. In some embodiments, the center lobe 1804 may be
constructed from nitinol filaments. In some embodiments, the center
lobe 1804 may be constructed from a mixture of nitinol and DFT
filaments. In some embodiments, the center lobe 1804 may comprise
filaments having a transverse dimension of between about 0.0009''
and about 0.0014''. In some embodiments, the center lobe 1804 may
comprise filaments having a transverse dimension of between about
0.001'' and about 0.00125''.
[0219] In some embodiments the distal lobe 1806 may be constructed
from between about 108 and about 180 filaments 1818. In some
embodiments, the distal lobe 1806 may be constructed from between
about 54 and about 90 nitinol filaments and between about 54 and
about 90 DFT filaments. In some embodiments, the DFT filaments may
comprise an outer, high-strength material such as nitinol, and an
inner core of a highly radiopaque material, such as platinum,
platinum alloy such as 90% platinum/10% iridium, or gold or
tantalum. In some embodiments, the DFT filaments may comprises a
cross-sectional fill area ratio of between about 10% and about 50%
of the highly radiopaque material. In some embodiments, the DFT
filaments may comprises a cross-sectional fill area ratio of
between about 20% and about 40% of the highly radiopaque material.
In some embodiments, the DFT filaments may comprises a
cross-sectional fill area ratio of between about 25% and about 35%
of the highly radiopaque material. In some embodiments, the distal
lobe 1806 may comprises nitinol filaments having a transverse
dimension or diameter of between about 0.004'' and about 0.0006'',
and DFT filaments having a transverse dimension of between about
0.0006'' and about 0.0009''. In some embodiments, the distal lobe
1806 may comprise about 72 nitinol filaments having a transverse
dimension, of about 0.0005'' and about 72 DFT filaments having a
transverse dimension of about 0.00075''. In some embodiments, the
distal lobe 1806 may have an additional distal hub (and thus not be
made with the castellated mandrel). In these embodiments, the
additional distal hub may be radiolucent, and thus allow
visualization on x-ray or fluoroscopy. In these embodiments, the
filaments may be mostly or all nitinol.
[0220] In some embodiments, the multi-lobe mesh device 1800 may be
constructed so that the proximal lobe 1802 has an expanded state
having a first diameter D.sub.1, the center lobe 1804 has an
expanded state having a second diameter D.sub.2, and the distal
lobe 1806 has an expanded state having a third diameter D.sub.3. In
some embodiments, the three diameters D.sub.1, D.sub.2, D.sub.3 may
be approximately equal to each other. In some embodiments, first
diameter D.sub.1 and the second diameter D.sub.3 may be less than
the second diameter D.sub.2 in order to allow the multi-lobe mesh
device 1800 to conform to the shape of a vascular defect 160, such
as an aneurysm. Turning to FIG. 46, the multi-lobe mesh device 1800
is shown in a radially constrained state for delivery along a
longitudinal axis 1828 through a microcatheter 61. The multi-lobe
mesh device 1800 is releasably coupled to a delivery apparatus 1822
at its proximal end 1824. The distal end 1820 of the multi-lobe
device 1800 in its radially constrained state corresponds to a
distal extremity of the distal lobe 1806. The serial array 1826 of
the three lobes 1802, 1804, 1806 assures that upon delivery, there
are no layer overlaps that would increase profile. The multi-lobe
mesh device 1800 thus has a small radially constrained profile, and
may be deliverable through microcatheter 61 having an inner
diameter as small as 0.021'' and even as small as 0.017''.
[0221] FIG. 47 illustrates an embodiment of the multi-lobe mesh
device 1800 after being delivered into a vascular defect 160. The
distal lobe 1806 has been delivered so that it is located adjacent
to a rupture site 163. An appropriate size of the multi-lobe mesh
device 1800 has been chosen so that the center lobe 1804 is
expanded within the vascular defect 160, giving it mechanical
support. The proximal lobe 1802 has been delivered so that it is
expanded across the neck 167. The relatively short longitudinal
distance between the proximal hub 1808 and the center hub 1810, the
relatively short longitudinal distance between the center hub 1810
and the distal hub 1812, and even the relatively short longitudinal
distance between the distal hub 1812 and the distal end 1820, all
serve to decrease the potential for the multi-lobe mesh device 1800
to undergo longitudinal compression leading to in vivo compaction.
This longitudinal compression/compaction is sometimes referred to
as clot contraction, and has been described by some as somewhat
analogous to the shrinkage that occurs in a wound upon healing.
Longitudinal compression of a mesh device 1850 is demonstrated in
FIGS. 49-51. After implantation, compressive forces F.sub.LC from a
number of different biological sources may decrease the overall
length L.sub.O of the mesh device 1850 over time (from FIG. 49 to
FIG. 51, L1.sub.O1, L.sub.O2, L.sub.O3), by forcing the distal
internal end 1852 and/or the proximal internal end 1854 to approach
each other while some inversion of the mesh device 1850 occurs,
thus decreasing the inner length (seen in FIGS. 49-51 as IL.sub.1,
IL.sub.2, IL.sub.3). In some embodiments of the mesh device 1850,
this may occur at longitudinal compressive forces F.sub.LC as low
as 0.2 Newton, and even 0.1 Newton. Because the normal expanded
configuration of the multi-lobe mesh device 1800 of FIGS. 45-47 has
lobes 1802, 1804, 1806 that approximate partial longitudinal
compression, additional longitudinal compression is less likely to
occur. In some embodiments, the distal lobe 1806 may have an
additional distal hub (and thus not be made with the castellated
mandrel). In these embodiments, the additional distal hub may be
radiolucent, and thus allow visualization on x-ray or fluoroscopy.
In these embodiments, the filaments may be mostly or all
nitinol.
[0222] FIG. 48 illustrates an embodiment of a multi-lobe mesh
device 1900 having a proximal lobe 1902 and a support lobe 1904.
The filaments 1910 of the proximal lobe 1902 and the filaments 1912
of the support lobe 1904 are secured to each other by a distal hub
1908. In some embodiments, a proximal hub 1906 secures the
filaments 1910 of the proximal lobe 1902 at its proximal end 1914.
In some embodiments, the proximal lobe 1902 may be constructed in a
similar fashion and with similar materials as the proximal lobe
1802 of the multi-lobe mesh device 1800 of FIGS. 45-47. In some
embodiments, the support lobe 1904 may be constructed in a similar
fashion and with similar materials as the center lobe 1804 of the
multi-lobe mesh device 1800 of FIGS. 45-47. In some embodiments, as
shown in FIG. 48, the support lobe 1904 of the Multi-lobe mesh
device 1900 may be constructed without a hub at its distal end, as
may the distal lobe 1806 of the multi-lobe mesh device 1800. In
both cases, this may be done to protect the dome 161 of an aneurysm
(vascular defect 160). The support lobe 1904 is configured to
provide both radial support and longitudinal support within the
vascular defect 160. In some embodiments, the support lobe 1904 may
have an additional distal hub (and thus not be made with the
castellated mandrel). In these embodiments, the additional distal
hub may be radiolucent, and thus allow visualization on x-ray or
fluoroscopy. In these embodiments, the filaments may be mostly or
all nitinol. As described, in the multi-lobe mesh device 1800 of
FIG. 47, the proximal lobe 1802 may be made with a relatively
smaller porosity than the center lobe 1804, for the purpose of
minimizing blood flow at the neck 167 of the aneurysm 160. The
distal lobe 1806 may also have a lower porosity than the center
lobe 1804 in order to inhibit rebleeding and/or accelerate healing
at the rupture site 167. In some embodiments, the center lobe 1804
is constructed from larger diameter filaments than either the
proximal lobe 1802 or the distal lobe 1806. This construction may
allow the center lobe 1804 to provide increased radial stiffness at
the center portion of the aneurysm 160, for example, to maintain
the position of the multi-lobe mesh device 1800 within the
aneurysm. Any of the three lobes 1802, 1804, 1806 may be
constructed of filaments 1814, 1816, 1818 having more than one
material and/or more than one diameter or transverse dimension. In
the multi-lobe mesh device 1900 of FIG. 48, the proximal lobe 1902
may be made with a relatively smaller porosity than the support
lobe 1904, for the purpose of minimizing blood flow at the neck 167
of the aneurysm 160. In some embodiments, the support lobe 1904 is
constructed from larger diameter filaments than the proximal lobe
1902. This construction may allow the support lobe 1904 to provide
increased radial stiffness at the center portion of the aneurysm
160, for example, to maintain the position of the multi-lobe mesh
device 1900 within the aneurysm. Either of the two lobes 1902, 1904
may be constructed of filaments 1910, 1912 having more than one
material and/or more than one diameter or transverse dimension.
[0223] FIG. 52 illustrates an embodiment of a multi-lobe mesh
device 2000 having a proximal lobe 2002 and a support lobe 2004
that was constructed in accordance with an embodiment of the
present invention. The multi-lobe mesh device 2000 has a proximal
hub 2006 which secures the proximal ends 2012 of filaments 2014 of
the proximal lobe 2002, a center hub 2008 which secures both the
distal ends 2016 of the filaments 2014 of the proximal lobe 2002
and the proximal ends 2018 of the filaments 2020 of the support
lobe 2004, and a distal hub 2010 which secures the distal ends 2022
of the filaments 2020 of the support lobe 2004. The multi-lobe mesh
device 2000 is releasably secured to a delivery apparatus 2024. The
multi-lobe mesh device 2000 was constructed with a relaxed,
expanded diameter D of 7 mm. The proximal lobe 2012 was constructed
using a combination of 72 nitinol filaments having a diameter of
0.0005'' and 72 DFT filaments (nitinol outer shell with a platinum
core) having a diameter of 0.00075''. The support lobe 2004 was
constructed using 54 DFT filaments (nitinol outer shell with a
platinum core) having a diameter of 0.00125''. After assembly, the
multi-lobe mesh device 2000 was successfully passed through a
0.017'' diameter inner lumen of a microcatheter 61 (VIA-17 produced
by Sequent Medical, Inc., Aliso Viejo, Calif.). In comparison,
standard single-lobe mesh devices having a length equivalent to the
total length L of the two lobes 2002, 2004 of the multi-lobe mesh
device are currently not able to pass through a 0.017'' diameter
inner lumen, and require a 0.021'' diameter inner lumen. Actually,
the collapsed profile of the support lobe 2004 is approximately
0.013'' and the collapsed profile of the proximal lobe 2002 is
approximately 0.011''. In some embodiments, the diameter of the
hubs 2006, 2018, 2010 is approximately 0.016''. In the multi-lobe
mesh device 2000 of FIG. 52, the proximal lobe 2002 may be made
with a relatively smaller porosity than the support lobe 2004. In
some embodiments, the support lobe 2004 is constructed from larger
diameter filaments than the proximal lobe 2002. This construction
may allow the support lobe 1904 to provide increased radial
stiffness at the center portion of an aneurysm 160, for example, to
maintain the position of the multi-lobe mesh device 2000 within the
aneurysm. Either of the two lobes 2002, 2004 may be constructed of
filaments 2014, 2020 having more than one material and/or more than
one diameter or transverse dimension.
[0224] FIGS. 53-56 illustrate the in vitro delivery (simulated use)
of the multi-lobe mesh device 2000 through the microcatheter 61
(VIA-17). The distal tip 69 is indicated in each of the four
figures. In FIG. 53, the support lobe 2004 begins to expand as it
is pushed out of the distal tip 69 of the microcatheter 61. In FIG.
54 the support lobe 2004 reaches its relaxed expanded diameter. In
a vascular defect 160. The support lobe 2004 may riot reach its
fully relaxed expanded diameter, because the vascular defect itself
may apply some compression on the support lobe 2004. In FIG. 55,
the proximal lobe 2002 begins to expand as it is pushed out of the
distal tip 69 of the microcatheter 61. In FIG. 56, the proximal
lobe reaches its relaxed expanded diameter. In a vascular defect
160, the proximal lobe 2002 may not reach its fully relaxed
expanded diameter, because the vascular defect itself may apply
some compression on the proximal lobe 2002.
[0225] FIGS. 57A-58 illustrate an embodiment of a multi-lobe mesh
device 2140 having a proximal lobe 2142 and a distal lobe 2144. The
filaments 2146 of the proximal lobe 2142 and the filaments 2148 of
the distal lobe 2144 are secured to each other by a support member
2150. In some embodiments, a proximal hub 2152 secures the
filaments 2146 of the proximal lobe 2142 at its proximal end 2154.
In some embodiments, the proximal lobe 2142 may be constructed in a
similar fashion and with similar materials as the proximal lobe
1802 of the multi-lobe mesh device 1800 of FIGS. 45-47. In some
embodiments, the distal lobe 2144 may be constructed in a similar
fashion and with similar materials as the center lobe 1804 of the
multi-lobe mesh device 1800 of FIGS. 45-47. In some embodiments,
the distal lobe 2144 of the multi-lobe mesh device 2140 may be
constructed without a hub at its distal end 2155 (FIG. 59). This
may be done to protect the dome 161 of an aneurysm (vascular defect
160). A support member 2150 is positioned between the proximal lobe
2142 and distal lobe 2144.
[0226] The distal lobe 2144 may have a generally convex shape at
its distal end. The proximal lobe 2142 may have a generally convex
shape at its proximal end. The support member 2150 is positioned
between the distal and proximal lobes 2144, 2142. The expanded
states of the distal and proximal lobes 2144, 2142 define a
toroidal cavity 2151 through which the support member 2150
extends.
[0227] In some embodiments, the support member 2150 may comprise a
substantially rigid cylindrical member. In some embodiments, the
support member 2150 may comprises a hypo tube. Rigidity in the
support member 2150 may aid in maintaining a longitudinal axis 2156
of the proximal lobe 2142 and a longitudinal axis 2158 of the
distal lobe 2144 at a generally fixed angle to each other, when the
proximal lobe 2142 and the distal lobe 2144 are each in their
expanded configurations. Rigidity in the support member 2150 may
aid in maintaining the longitudinal axis 2156 of the proximal lobe
2142 and the longitudinal axis 2158 of the distal lobe 2144
substantially parallel to each other, when the proximal lobe 2142
and the distal lobe 2144 are each in their expanded configurations.
Rigidity in the support member 2150 may aid in maintaining the
longitudinal axis 2156 of the proximal lobe 2142 and the
longitudinal axis 2158 of the distal lobe 2144 substantially
collinear with each other, when the proximal lobe 2142 and the
distal lobe 2144 are each in their expanded configurations.
Maintenance of alignment between the proximal lobe 2142 and the
distal lobe 2144 can aid "fit" of the multi-lobe mesh device 2140
within an aneurysm. In some, embodiments it can aid fit within an
aneurysm having a generally symmetric shape.
[0228] In some embodiments, the distal lobe 2144 may have an
additional distal hub (and thus not be made with the castellated
mandrel). In these embodiments, the additional distal hub may be
radiolucent, and thus allow visualization on x-ray or fluoroscopy.
In these embodiments, the filaments may be mostly or all nitinol.
The resistance to force that the support member 2150 provides may
limit the effects of "dot compression" as described herein. In
embodiment of FIGS. 57A-58, the support member 2150 constructed
from a hypo tube supplies rigid axial support against both
compressive forces and tensile forces between the proximal end 2163
of the distal lobe 2144 and the distal end 2165 of the proximal
lobe 2142.
[0229] Turning to FIG. 59, the multi-lobe mesh device 2140 is shown
in a radially constrained state for delivery along a longitudinal
axis 2158 through a microcatheter 61. The multi-lobe mesh device
2140 is releasably coupled to a delivery apparatus 2153 at its
proximal end 2154. The distal end 2.155 of the multi-lobe device
2140 in its radially constrained state corresponds to a distal
extremity of the distal lobe 2144. The serial array 2157 of the two
lobes 2142, 2144 and the support member 2150 assures that upon
delivery, there are no layer overlaps that would increase profile.
The multi-lobe mesh device 21400 thus has a small radially
constrained profile, and may be delivered through microcatheter 61
having an inner diameter as small as 0.021'' and even as small as
0.017''.
[0230] In FIG. 60, a multi-lobe mesh device 2640 having similar
characteristics and components to the multi-lobe mesh device 2140
of FIGS. 57A-59 is shown, but the support member 2650 of the
multi-lobe mesh device 2540 comprises a coil 2659. The coil 2659
may be constructed of stainless steel, nitinol, or other suitable
materials, or may be constructed twin radiopaque material, such as
platinum or platinum alloys. In some embodiments, the coil 2659
supplies rigid axial support against compressive forces, while
allowing for some longitudinal separation or elongation between the
proximal lobe 2642 and the distal lobe 2644. In some embodiments,
the coil 2659 is an extension spring that applies a bias between
the proximal lobe 2642 and the distal lobe 2644, forcing them
together,. When the extension spring is at rest, the extension
spring is not compressible to a smaller length i.e., each winding
of the spring is in contact with adjacent windings at first and
second circumferential points on each winding. This may aid the
manufacture of the multi-lobe mesh device 2640, allowing the
extension spring to be held in an at least partially extended
configuration, with at least some space between winds in the spring
while the distal end 2665 of the proximal lobe 2642 is attached to
the proximal end 2567 of the extension spring and the proximal end
2663 of the distal lobe 2644 is attached to the distal end 2669 of
the extension spring. After assembly of the extension spring with
the proximal lobe 2642 and the distal lobe 2544, the extension
spring serves to align the proximal lobe 2642 with the distal lobe
2.644 and hold them adjacent to each other at a central portion
2673. When the multi-lobe mesh device 2640 is placed through a
microcatheter having a tortuous shape, the coil 2659 adds
flexibility, thus requiring less force to push the multi-lobe mesh
device 2640 through the microcatheter. The multi-lobe mesh device
2640 having a coil 2659 as the support member 2650 is also more
pliable and when delivered into an aneurysm may provide improved
safety. The multi-lobe mesh device 2640 having a coil 2659 as the
support member 2650 may also be more easily oriented and aligned
within aneurysms having irregular shapes.
[0231] As illustrated in FIG. 61, modular braid density (BD.sub.M)
is a two-dimensional representation of the percent area coverage of
filaments in a substantially diamond-shaped module 1008 within the
braid. Braid density (BD) as described herein is different from the
traditional "braid wire density" which is described in picks per
inch (PPI) or picks per centimeter. "Braid wire density" is net a
ratio of areas, but rather the number of wire crossings within a
particular length of a tubular section, "Braid wire density" is
blind to the amount of material coverage within a certain area,
because it does not take into account the wire diameter or
diameters. Braid density (BD), on the other hand, is specific to
the percent of material coverage within a certain area. The
substantially diamond-shaped module 1008 is a two-dimensional area
A.sub.O, inside the diamond-shaped dashed lines in FIG. 50D. The
substantially diamond-shaped module 1008 includes a substantially
diamond-shaped opening 1011 having an area A.sub.O, which is
surrounded by four filaments; a first filament 1013, a second
filament 1015, a third filament 1017, and a fourth filament 1019.
As will be described, further, the four filaments 1013, 1015, 1017,
1019 may comprise four individual wires, or alternatively, two or
more filaments may be made from the same wire. The four filaments
1013, 1015, 1017, 1019 cross each other around the diamond-shaped
opening 1011 at a first crossing 1023 between first filament 1013
and second filament 1015, a second crossing 1025 between second
filament 1015 and third filament 1017, a third crossing 1027
between third filament 1017 and fourth filament 1019, and a fourth
crossing 1029 between fourth filament 1019 and first filament 1013.
The area A.sub.M within the diamond-shaped module 1008 and the area
A.sub.O within the diamond-shaped opening 1011 may each be
approximated by the formula for area of a parallelogram (base
multiplied by height, where height is perpendicular to the base).
The four dashed lines in FIG. 61 are each centered between the two
outer extents of the filament transverse thickness (e.g., filament
width or circular filament diameter). Therefore, the area A.sub.M
of the diamond-shaped module 1008 includes the area A.sub.O of the
diamond-shaped opening 1011 and the area of one-half of the
thickness of each of the four filaments 1013, 1015, 1017, 1019
surrounding the diamond-shaped opening 1011. As mentioned, two or
more of the filaments may have a different thickness from each
other, or all may be the same thickness. The modular braid density
(BD.sub.M) calculated at a single module is:
BD.sub.M=(A.sub.M-A.sub.O)/A.sub.M [0232] where A.sub.M is area of
the diamond-shaped module, and [0233] A.sub.O is the area of the
diamond-shaped opening.
[0234] In an embodiment of a braided tubular member having a fixed
diameter, fixed circumference, and a fixed number of filaments, the
number of diamond-shaped modules 1008 fitting within the fixed
circumference will not change, regardless of how sparsely or
densely the braid is formed. Therefore, the module width 1084 will
remain the same dimension, regardless of how sparsely or densely
the braid is formed. However, the module length 1086 will be
shorter as the braid is formed more densely, and the module length
1086 will be longer as the braid is formed more sparsely. During
braiding, to accommodate this change in the module length 1086
without a change in module width 1084, filament 1015 and filament
1017 will slide over one another at crossing 1025 and filament 1013
and filament 1019 will slide over one another at crossing 1029
while angle 1082 and the angle across from angle 1082 change. In
conjunction with this, filament 1013 and filament 1015 will swivel
in relation to one another at crossing 1023 and filament 1017 and
filament 1019 will swivel in relation to one another at crossing
1027 while angle 1078 and the angle across from angle 1078 change.
For example, as the braid is wound more densely, angle 1082 and the
angle across from angle 1082 will both increase while angle 1078
and the angle across from angle 1078 both decrease. Moreover, as
the braid is wound more sparsely, angle 1082 and the angle across
from angle 1082 will both decrease while angle 1078 and the angle
across from angle 1078 both increase. It should be noted that angle
1082 in braiding nomenclature would be two times the "braid
angle".
[0235] The increase or decrease in module length 1086 with braiding
"density" change, coupled with the constant module width 1084,
means that the number of modules in a certain circumferential "row"
will not change with a change in angles 1078, 1082, but the number
of modules in a certain axial "column" will change. To calculate
the cylindrical braid density (BD.sub.C), one must sum both the
numerators and denominators of all of the modular braid densities
within the cylindrical area having k modules, and then take the
ratio:
BDC=.SIGMA.(AMk-AOk)/.SIGMA.(A.sub.Mk) [0236] k=1, 2, 3, . . . , n
[0237] where A.sub.M is area of the diamond-shaped module, and
[0238] A.sub.O is the area of the diamond-shaped opening, and
[0239] In the case that there is some variance in the modular braid
densities (BD.sub.M) over a specific portion of a braided tubular
member, or a mesh device made from a braided tubular member, the
cylindrical braid density (BD.sub.C) may be calculated. A first
example of varying modular braid densities (BD.sub.M) is in a
transition portion 1003, where modular braid densities (BD.sub.M)
increase or decrease along the longitudinal axis Z.sub.L. A second
example of varying modular braid densities (BD.sub.M) is in a mesh
device having a spherical or globular shape, where the modular
braid densities (BD.sub.M) decrease towards the outer radius of the
mesh device and increase towards the center or longitudinal axis
Z.sub.L of the mesh device. It is assumed that the key braid
density (BD) in a braid portion that is located near the maximum
flow into a vascular defect, such as an aneurysm, is the braid
density (BD) at the most expanded diameter. The braid density (BD)
inherently becomes greater towards the central axis of the mesh
device, because the effective diameter (and thus circumference)
decreases, thus leaving less space for the same number of filaments
1005, and thus decreasing, the module width 1084 of each
module.
[0240] In several embodiments of mesh devices, the mesh device is
formed from a braided tubular member having at least two distinct
braided portions 1002, 1004, so that the mesh device itself may
have at least two distinct braided portions. One of the main
purposes of having at least two braided portions, is that a more
sparsely braided portion may be mechanically easier to
diametrically constrain for delivery within the small lumen of a
microcatheter 61 and provide a more flexible device for delivering
through a tortuous path, while a more densely braided portion may
be more effective in disrupting blood flow, for example, when the
more densely braided portion is placed at the neck or opening of an
aneurysm or other vascular defect. As the second braided portion
1004 is braided mote densely (i.e., with increased angle 1082 and
decreased angle 1078), the resistance to flow through the
diamond-shaped opening 1011 increases. The flow through a
diamond-shaped opening 1011 can be characterized by the hydraulic
diameter (D.sub.B) 1033, a theoretical circular diameter which
represents the same flow characteristics as the diamond-shaped
opening 1011. Hydraulic diameter (D.sub.H) is typically used to
represent flow through various non-circular lumens or openings,
like the diamond-shape opening 1011. This is because non-circular
openings may have low flow zones, like the low flow zone 1088 in
the diamond-shaped opening 1011. The formula for hydraulic diameter
(D.sub.B) is:
D.sub.H=(4.times.A.sub.O)/P.sub.O [0241] Where A.sub.O is the area
of the diamond-shaped opening, and [0242] P.sub.O is the perimeter
of the diamond-shaped opening.
[0243] Braid density (BD) may be used to compare one portion of the
braided tubular member to another portion of the braided tubular
member, Braid density (BD) may also be used to compare a portion
adjacent the longitudinal axis Z.sub.L of the braided tubular
member with the most expanded section within the same portion of
the braided tubular member. Braid density (BD) may be used to
compare one portion of a mesh device constructed from the braided
tubular member to another portion of the mesh device constructed
from the braided tubular member, for example, the most expanded
section of a first portion with the most expanded portion of a
second portion. As mentioned, the most expanded section of a
portion intended to disrupt flow (for example, at the neck of an
aneurysm), is relevant in predicting the effectiveness in
disrupting flow in a worst-case, high flow location. Braid density
may also be represented as the average (i.e., mean, median) of
several different portions of a braided tubular member of a mesh
device made from the braided tubular member. Braid density may also
be represented as the average of measurements of the same portion
of several braided tubular members or mesh devices constructed from
braided tubular members.
Thrombus Removal
[0244] FIGS. 62 and 63 illustrate a thrombus removal device 2400
having a self-expanding structure 2402 at its distal end 2404.
Patients exhibiting ischemic stroke often have thrombi blocking
blood flow to portions of the brain. Removal of these thrombi can
allow recovery of symptoms, and can even be life-saving. The
self-expanding structure 2402 is secured to an elongate shaft 2406
and has a radially constrained configuration for delivery through a
microcatheter or sheath, and an expanded configuration (as shown in
FIGS. 62 and 63). The self-expanding structure 2402 includes a
cylindrical engagement structure 2408 and a trapping structure
2410. The cylindrical engagement structure 2408 is configured to
engage thrombus within its boundaries, and the trapping structure
2410 is located at the distal end of the cylindrical engagement
structure 2410 and is configured to maintain the captured thrombus
within the cylindrical engagement structure 2408 as the thrombus
removal device 2400 is removed from the patient.
[0245] The cylindrical engagement structure 2408 has a distal end
2415 and a proximal end 2416, and is formed from several wires
2412, in some embodiments, about 10 to about 18 wires, or about 12
wires. In some embodiments, the cylindrical engagement structure
2408 is formed from nitinol wire. In other embodiments the
cylindrical engagement structure 2408 is formed from
Cobalt-Chromium alloys or stainless steel. In some embodiments, the
transverse dimension or diameter of the wire is between about
0.0008'' and 0.0035'', or about 0.001'' to about 0.003'', or about
0.002''. In some embodiments, the wires 2412 may be formed into the
cylindrical engagement structure 2408 by hand or by use or and
automated or partially-automated braiding apparatus and process,
such as the braiding apparatus and process described in the
commonly assigned U.S. Pat. No. 8,261,648, "Braiding Mechanism and
Methods of Use" by Marchand et al., which is herein incorporated by
reference in its entirety for all purposes. The wires 2412 are
secured at the distal end 2415 of the cylindrical engagement
structure 2408 by a distal hub 2414 and are secured at the proximal
end 2416 by a proximal band 2418. Turning to FIG. 63, the
cylindrical engagement structure 2408 includes wires 2412a-p which
are wound to each other with a series of twists 2420a-N, where
N=the total number of twists 2420. In FIG. 63, the twists 2420 are
shown as one complete turn, or 360.degree., but other parameters
may be used to make cylindrical engagement structures 2408 of
varying embodiments two complete turns, one and one-half turn). By
varying the number of turns, the length L.sub.T of each twist 2420
may be varied. The length L.sub.T may range from about 0.25 mm to
about 3 mm, or about 0.35 mm to about 1 nun, or about 0.5 mm.
Following the particular wire 2412b from a location near the distal
end 2404 and moving proximally, wire 2412b is wound with wire 2412a
at twist 2420f. Wire 2412b is then wound with wire 2412c at twist
2420b Wire 2412b is then wound with wire 2412e at twist 2420c.
Because of the full (360.degree.) turn, wire 2412b continues
following a general spiral pattern as it is wound with the other
wires 2412. Other wires, like 2412a and 2412e follow a general
spiral pattern, but in the opposite direction of the general spiral
pattern of wire 2412b. In certain other embodiments, the twists may
be varied in terms of the total number of turns, for example, half
turn increments, which allow a variety of other structures to be
formed. In some embodiments, braid angle .beta. may be varied along
the length of the longitudinal axis Z.sub.L. Braid angle .beta. is
one-half of the angle between two twisted wires (e.g., 2412b and
2412c) as they extend from a twist (e.g., 2420b).
[0246] Because the wires 2412 are held together at the twists 2420,
the cylindrical engagement structure 2408 is durable and maintains
its expanded shape as it engages with thrombus, meets the blood
vessel will, and is pulled through the blood vessel. The trapping
structure 2410 may comprise a braided mesh structure comprising
filaments 2424 that are secured at their ends by the distal hub
2414 and a proximal hub 2426. The braided mesh structure 2422 has a
radially constrained configuration for delivery through a
microcatheter. In some embodiments, the trapping structure 2410 may
be located entirely within the cylindrical engagement structure
2408. In some embodiments, the transverse dimension or diameter of
the filaments 2424 is between about 0.0005'' and 0.002'' or about
0.00075' to about 0.0015'', or about 0.001''. Both the cylindrical
engagement structure 2408 and the trapping structure 2410 may be
heat formed to maintain their shape. In some embodiments, this may
be done at a temperature of around 500.degree. C. In some
embodiments, the cylindrical engagement structure 2408 and the
trapping structure may each be heat formed separately from one
another. In some embodiments, the cylindrical engagement structure
2408 and the trapping structure 2410 may be heat formed
together.
[0247] The braided mesh structure 2422 of the trapping structure
2410 has an expanded configuration (as seen in FIGS. 62 and 63)
having a braid density BD sufficiently high enough to maintain
thrombus within the cylindrical engagement structure 2408 as the
thrombus removal device 2400 is pulled proximally through a blood
vessel or through another catheter (guiding catheter, delivery
sheath, etc.). The conformity of the cylindrical engagement
structure 2408 to the vessel wall combined with the inability for
thrombus to pass through the trapping structure 2410 combine to
create a compartment 2417 to trap thrombus and shuttle it
proximally. In some cases, the thrombus removal device 2400 is
pulled into a microcatheter after being used to remove thrombus
from a blood vessel. In some cases, the thrombus removal device
2400 is pulled only into a larger catheter or sheath after being
used to remove thrombus from a blood vessel. In some cases, the
thrombus removal device 2400 is pulled along with a microcatheter
into a larger catheter or sheath after being used to remove
thrombus from a blood vessel. Another characteristic of the
trapping structure 2410 is that it may be made in some embodiments
with a braid density BD such that it is capable of trapping
thrombus, while simultaneously allowing normal blood to flow
through, for example, to perfuse distal vasculature and end
tissue.
[0248] FIGS. 64-67 illustrate the thrombus removal device 2400 in
use to remove a thrombus 2430 from a blood vessel 2428. A catheter
2432 is delivered so that its distal end 2419 is distal to the
thrombus 2430 as in FIG. 64, or adjacent the distal end 2421 of the
thrombus 2430, and the thrombus removal device 2400 is pushed out
of the catheter 2432 such that the trapping structure 2410 expands
and is located distal the thrombus and cylindrical engagement
structure 2408 expands around and encompasses the thrombus 2430
(FIG. 65). The thrombus removal device 2400 is pulled proximally
into the catheter 2432, trapping the thrombus 2430 (FIG. 66) and
the thrombus removal device 2400 is removed (FIG. 67).
[0249] Although the foregoing invention has, for the purposes of
clarity and understanding, been described in some detail by way of
illustration and example, it will be obvious that certain changes
and modifications may be practiced which will still fall within the
scope of the appended claims.
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