U.S. patent application number 11/398082 was filed with the patent office on 2006-08-17 for microcoil vaso-occlusive device with multi-axis secondary configuration.
This patent application is currently assigned to MICROVENTION, INC.. Invention is credited to Brian J. Cox, David A. Ferrera, Matthew Fitz, George R. JR. Greene, Robert F. Rosenbluth, Dean Schaefer.
Application Number | 20060184196 11/398082 |
Document ID | / |
Family ID | 21929738 |
Filed Date | 2006-08-17 |
United States Patent
Application |
20060184196 |
Kind Code |
A1 |
Schaefer; Dean ; et
al. |
August 17, 2006 |
Microcoil vaso-occlusive device with multi-axis secondary
configuration
Abstract
A vaso-occlusive device includes a microcoil formed into a
minimum energy state secondary configuration comprising a plurality
of curved segments, each defining a discrete axis, whereby the
device, in its minimum energy state configuration, defines multiple
axes. In a preferred embodiment, the secondary
configuration-comprises a plurality of interconnected closed loops
defining a plurality of discrete axes. In a second embodiment, the
secondary configuration defines a wave-form like structure
comprising an array of laterally-alternating open loops defining a
plurality of separate axes. In a third embodiment, the secondary
configuration forms a series of tangential closed loops, wherein
the entire structure subtends a first angle of arc, and wherein
each adjacent pair of loops defines a second angle of arc. In a
fourth embodiment, the secondary configuration forms a logarithmic
spiral. In all embodiments, the device, in its secondary
configuration, has a dimension that is substantially larger than
the largest dimension of the vascular site (i.e., aneurysm) in
which it is to be deployed. Thus, confinement of the device within
an aneurysm causes it to assume a three-dimensional configuration
with a higher energy state than the minimum energy state. Because
the minimum energy state configuration of the device is larger (in
at least one dimension) than the aneurysm, the deployed device is
constrained by its contact with the walls of the aneurysm from
returning to its minimum energy state configuration. The engagement
of the device with the aneurysm wall minimizes shifting or tumbling
due to blood flow. Furthermore, the secondary configuration is not
conducive to "coin stacking," thereby minimizing the compaction
experienced.
Inventors: |
Schaefer; Dean; (Laguna
Hills, CA) ; Cox; Brian J.; (Laguna Niguel, CA)
; Greene; George R. JR.; (Costa Mesa, CA) ;
Ferrera; David A.; (Manhattan Beach, CA) ; Fitz;
Matthew; (Encinitas, CA) ; Rosenbluth; Robert F.;
(Laguna Niguel, CA) |
Correspondence
Address: |
KLEIN, O'NEILL & SINGH
2 PARK PLAZA
SUITE 510
IRVINE
CA
92614
US
|
Assignee: |
MICROVENTION, INC.
Aliso Viejo
CA
|
Family ID: |
21929738 |
Appl. No.: |
11/398082 |
Filed: |
April 5, 2006 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
10043947 |
Jan 11, 2002 |
7033374 |
|
|
11398082 |
Apr 5, 2006 |
|
|
|
09671021 |
Sep 26, 2000 |
6605101 |
|
|
10043947 |
Jan 11, 2002 |
|
|
|
Current U.S.
Class: |
606/200 |
Current CPC
Class: |
A61B 17/12022 20130101;
A61B 17/12145 20130101; A61B 2017/00867 20130101; A61B 2017/00526
20130101; A61B 17/12113 20130101 |
Class at
Publication: |
606/200 |
International
Class: |
A61M 29/00 20060101
A61M029/00 |
Claims
1-45. (canceled)
46. A vaso-occlusive device comprising a filamentous structure
formed into a minimum energy state secondary configuration
comprising at least two substantially coplanar loops.
47. The vaso-occlusive device of claim 1, wherein the device in its
secondary configuration resembles a series of interconnected curved
segments defined by coplanar radii.
48. The vaso-occlusive device of claim 2, wherein the device in its
secondary configuration resembles nearly, but not fully completed
circles.
49. The vaso-occlusive device of claim 1, wherein the device in its
secondary configuration resembles a series of interconnected curved
segments defined by radii that lie in different planes intersecting
a sphere.
50. The vaso-occlusive device of claim 4, wherein the device in its
secondary configuration resembles helical loops.
51. The vaso-occlusive device of claim 1, wherein the filamentous
structure comprises a microcoil.
52. The vaso-occlusive device of claim 1, further comprising curved
segments which are substantially closed loops interconnected to
each other.
53. The vaso-occlusive device of claim 7, wherein the closed loops
are arranged tangentially to each other.
54. The vaso-occlusive device of claim 1, wherein the device is
dimensioned for installation in a vascular site having a
predetermined maximum dimension, and wherein the device, in its
secondary configuration, has at least one curved segment having a
diameter that is approximately equal to the maximum diameter of the
vascular site.
55. The vaso-occlusive device of claim 1, wherein the device is
dimensioned for installation in a vascular site having a
predetermined maximum dimension, and wherein the device, in its
secondary configuration, has a length that is at least twice the
maximum dimension of the vascular site.
56. A vaso-occlusive device comprising a filamentous structure
formed into a minimum energy state secondary configuration
comprising a plurality of curved segments comprising substantially
closed loops, interconnected to each other, wherein the entire
device subtends a first angle of arc and wherein each adjacent pair
of loops defines a second angle of arc between them.
57. The vaso-occlusive device of claim 11 wherein the second angle
of arc is less than about half the first angle of arc.
58. The vaso-occlusive device of claim 11 wherein the first angle
of arc is greater than about 30.degree..
59. The vaso-occlusive device of claim 11 wherein the first angle
of arc is greater than about 30.degree. and the second angle of arc
is less than about half the first angle of arc.
60. A vaso-occlusive device comprising a filamentous structure
formed into a minimum energy state secondary configuration
comprising a plurality of curved segments comprising substantially
closed loops, interconnected to each other, wherein the entire
device subtends a first angle of arc which is greater than about
30.degree. and wherein each adjacent pair of loops defines a second
angle of arc between them which is less than about half the first
angle of arc.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a Continuation-in-Part of co-pending
application Ser. No. 09/671,021; filed Sep. 26, 2000.
FEDERALLY-SPONSORED RESEARCH OR DEVELOPMENT
[0002] Not Applicable
BACKGROUND OF THE INVENTION
[0003] This invention relates generally to the field of vascular
occlusion devices and methods. More specifically, it relates to an
apparatus and method for occluding a blood vessel by embolizing a
targeted site (such as an aneurysm) in the blood vessel.
[0004] The embolization of blood vessels is desired in a number of
clinical situations. For example, vascular embolization has been
used to control vascular bleeding, to occlude the blood supply to
tumors, and to occlude vascular aneurysms, particularly
intracranial aneurysms. In recent years, vascular embolization for
the treatment of aneurysms has received much attention. Several
different treatment modalities have been employed in the prior art.
U.S. Pat. No. 4,819,637--Dormandy, Jr. et al., for example,
describes a vascular embolization system that employs a detachable
balloon delivered to the aneurysm site by an intravascular
catheter. The balloon is carried into the aneurysm at the tip of
the catheter, and it is inflated inside the aneurysm with a
solidifying fluid (typically a polymerizable resin or gel) to
occlude the aneurysm. The balloon is then detached from the
catheter by gentle traction on the catheter. While the balloon-type
embolization device can provide an effective occlusion of many
types of aneurysms, it is difficult to retrieve or move after the
solidifying fluid sets, and it is difficult to visualize unless it
is filled with a contrast material. Furthermore, there are risks of
balloon rupture during inflation and of premature detachment of the
balloon from the catheter.
[0005] Another approach is the direct injection of a liquid polymer
embolic agent into the vascular site to be occluded. One type of
liquid polymer used in the direct injection technique is a rapidly
polymerizing liquid, such as a cyanoacrylate resin, particularly
isobutyl cyanoacrylate, that is delivered to the target site as a
liquid, and then is polymerized in situ. Alternatively, a liquid
polymer that is precipitated at the target site from a carrier
solution has been used. An example of this type of embolic agent is
a cellulose acetate polymer mixed with bismuth trioxide and
dissolved in dimethyl sulfoxide (DMSO). Another type is ethylene
glycol copolymer dissolved in DMSO. On contact with blood, the DMSO
diffuses out, and the polymer precipitates out and rapidly hardens
into an embolic mass that conforms to the shape of the aneurysm.
Other examples of materials used in this "direct injection" method
are disclosed in the following U.S. Pat. No. 4,551,132--Pasztor et
al.; U.S. Pat. No. 19 4,795,741--Leshchiner et al.; U.S. Pat. No.
5,525,334--Ito et al.; and U.S. Pat. No. 5,580,568--Greff et
al.
[0006] The direct injection of liquid polymer embolic agents has
proven difficult in practice. For example, migration of the
polymeric material from the aneurysm and into the adjacent blood
vessel has presented a problem. In addition, visualization of the
embolization material requires that a contrasting agent be mixed
with it, and selecting embolization materials and contrasting
agents that are mutually compatible may result in performance
compromises that are less than optimal. Furthermore, precise
control of the deployment of the polymeric embolization material is
difficult, leading to the risk of improper placement and/or
premature solidification of the material. Moreover, once the
embolization material is deployed and solidified, it is difficult
to move or retrieve.
[0007] Another approach that has shown promise is the use of
thrombogenic microcoils. These microcoils may be made of a
biocompatible metal alloy typically platinum and tungsten) or a
suitable polymer. If made of metal, the coil may be provided with
Dacron fibers to increase thrombogenicity. The coil is deployed
through a microcatheter to the vascular site. Examples of
microcoils are disclosed in the following U.S. Pat. No.
4,994,069--Ritchart et al.; U.S. Pat. No. 5,122,136--Guglielmi et
al.; U.S. Pat. No. 5,133,731--Butler et al.; U.S. Pat. No.
5,226,911--Chee et al.; U.S. Pat. No. 5,304,194--Chee et al.; U.S.
Pat. No. 5,312,415--Palermo; U.S. Pat. No. 5,382,259--Phelps et
al.; U.S. Pat. No. 5,382,260--Dormandy, Jr. et al.; U.S. Pat. No.
5,476,472--Dormandy, Jr. et al.; U.S. Pat. No. 5,578,074--Mirigian;
U.S. Pat. No. 5,582,619--Ken; U.S. Pat. No. 5,624,461--Mariant;
U.S. Pat. No. 5,639,277--Mariant et al.; U.S. Pat. No.
5,658,308--Snyder; U.S. Pat. No. 5,690,667--Gia; U.S. Pat. No.
5,690,671--McGurk et al.; U.S. Pat. No. 5,700,258--Mirigian et al.;
U.S. Pat. No. 5,718,711--Berenstein et al.; U.S. Pat. No.
5,891,058--Taki et al.; U.S. Pat. No. 6,013,084--Ken et al.; U.S.
Pat. No. 6,015,424--Rosenbluth et al.; and U.S. Pat. Des. No.
427,680--Mariant et al.
[0008] While many prior art microcoil devices have met with some
success in treating small aneurysms with relatively narrow necks,
it has been recognized that the most commonly used microcoil
vaso-occlusive devices achieve less than satisfactory results in
wide-necked aneurysms, particularly in the cerebrum. This has led
to the development of three-dimensional microcoil devices, such as
those disclosed in U.S. Pat. No. 5,645,558--Horton; U.S. Pat. No.
5,911,731--Pham et al.; and U.S. Pat. No. 5,957,948--Mariant (the
latter two being in a class of devices known as "three-dimensional
Guglielmi detachable coils", or "3D-GDC's"). See, e.g., Tan et al.,
"The Feasibility of Three-Dimensional Guglielmi Detachable Coil for
Embolisation of Wide Neck Cerebral Aneurysms," Interventional
Neuroradiology, Vol. 6, pp. 53-57 (June, 2000); Cloft et al., "Use
of Three-Dimensional Guglielmi Detachable Coils in the Treatment of
Wide-necked Cerebral Aneurysms," American Journal of
Neuroradiology, Vol. 21, pp. 1312-1314 (August, 2000).
[0009] The typical three-dimensional microcoil is formed from a
length of wire that is formed first into a primary configuration of
a helical coil, and then into a secondary configuration that is one
of a variety of three-dimensional shapes. The minimum energy state
of this type of microcoil is its three-dimensional secondary
configuration. When deployed inside an aneurysm, these devices
assume a three-dimensional configuration, typically a somewhat
spherical configuration, that is at or slightly greater than, the
minimum energy state of the secondary configuration. Because the
overall dimensions of these devices in their non-minimum energy
state configuration is approximately equal to or smaller than the
interior dimensions of the aneurysm, there is nothing to constrain
the device from shifting or tumbling within the aneurysm due to
blood flow dynamics.
[0010] In some of these three-dimensional devices (e.g., U.S. Pat.
No. 5,122,136--Guglielmi et al.), the secondary configuration is
itself a helix or some similar form that defines a longitudinal
axis. Devices with what may be termed a "longitudinal" secondary
configuration form a three-dimensional non-minimum energy state
configuration when deployed inside an aneurysm, but, once deployed,
they have displayed a tendency to revert to their minimum energy
state configurations. This, in turn, results in compaction due to
"coin stacking" (i.e., returning to the secondary helical
configuration), thereby allowing recanalization of the
aneurysm.
[0011] There has thus been a long-felt, but as yet unsatisfied need
for a microcoil vaso-occlusive device that has the advantages of
many of the prior art microcoil devices, but that can be used
effectively to treat aneurysms of many different sizes
configurations, and in particular those with large neck widths. It
would be advantageous for such a device to be compatible for use
with existing guidewire and microcatheter microcoil delivery
mechanisms, and to be capable of being manufactured at costs
comparable with those of prior art microcoil devices.
SUMMARY OF THE INVENTION
[0012] Broadly, the present invention is a filamentous
vaso-occlusive device that has a minimum energy state secondary
configuration comprising a plurality of curved segments, whereby
the device, in its minimum energy state configuration, defines
multiple axes and/or foci. More specifically, each segment defines
either a plane and an axis that is substantially perpendicular to
the plane, or a path around the surface of a sphere, wherein the
path is defined by a unique locus located at the approximate center
point of the sphere around which the path is generated, and by a
radius extending from that locus that is equal to the radius of
that sphere.
[0013] In a particular preferred embodiment, the present invention
is an elongate microcoil structure having a minimum energy state
secondary configuration that defines a plurality or series of
tangentially-interconnected closed loops, preferably substantially
circular or elliptical, defining a plurality of separate axes. In
one form of the preferred embodiment, the closed loops are
substantially coplanar and define axes that are substantially
parallel. That is, the planes defined by the segments are
themselves substantially coplanar. In another form of the preferred
embodiment, each pair of adjacent loops defines a shallow angle,
whereby their respective axes define an angle of not more than
about 90.degree., and preferably not more than about 45.degree.,
between them. A further form of the preferred embodiment has the
tangential loops arranged so that the axis define by each loop is
orthogonal to a unique radius of a circle, the radii being
separated by a fixed angle of arc. In still another form of the
preferred embodiment, the loops, instead of being tangential,
overlap. In any of these forms, the loops may be of substantially
uniform diameter, or they may be of different diameters. For
example, the first and/or last loop in the series may be of a
smaller diameter than the other loops, or the loops may be in a
series of loops of progressively decreased diameter, optionally
with an additional small-diameter loop preceding the largest
diameter loop.
[0014] In first alternative embodiment, the microcoil structure has
a minimum energy state secondary configuration that defines a
wave-form like structure comprising a longitudinal array of
laterally-alternating open loops defining a plurality of separate
axes. In a specific construction of this embodiment, the wave-form
like structure defines a substantially sinusoidal waveform wherein
each of the maxima and minima of the waveform defines an arc of
radius r, and wherein each arc is connected to an adjacent arc by a
straight section of length L, wherein L is less than about 2r. As
in the preferred embodiment, the alternative embodiment may be in a
first form in which the loops are substantially coplanar and their
respective axes are substantially parallel, or in a second form in
which each pair of adjacent loops defines a shallow angle, whereby
their respective axes define an angle of not more than about
90.degree., and preferably not more than about 45.degree., between
them.
[0015] In a second alternative embodiment, the microcoil structure,
in its secondary configuration, forms a series of tangential closed
loops, preferably either substantially circular or elliptical,
wherein the entire structure subtends a first angle of arc, and
wherein each adjacent pair of loops defines a second angle of arc
between them. Preferably, the first angle is greater than about
30.degree., and the second angle is less than about half of the
first angle. It will be seen that each loop defines an axis, with
the angle formed by the axes of adjacent loops being the second
angle.
[0016] In a third alternative embodiment, the secondary
configuration of the microcoil structure forms preferably at least
two interconnected equiangular or logarithmic spirals, each
defining a single unique axis. As used in this specification, a
logarithmic or equiangular spiral is defined as a curve that cuts
all radii vectors at a constant angle. Specifically, if the curve
is a spiral, that is, a curve in which the radial vector R is a
monotonic increasing function of the radial angle .theta., the
spiral will be an equiangular spiral if the angle .alpha. formed
between a radial vector R and the tangent for any point P on the
spiral is constant. In equiangular spirals having an angle .alpha.
of greater than about 70.degree., the configuration begins to
resemble that of the shell of the chambered nautilus. In the
limiting case, it may be seen that a circle is an equiangular
spiral in which the angle .alpha. is 90.degree. (the radial vector
being a radius).
[0017] In a fourth alternative embodiment, the secondary
configuration of the microcoil structure resembles a series of
interconnected complex curved segments, each of which is defined by
a path around the surface of a sphere. Each of the segments is thus
defined by a unique focus located at the approximate center point
of the sphere around which the path is generated, and by a radius
extending from that locus that is equal to the radius of that
sphere. Each segment may be defined by radii that are coplanar (in
the case of a segment that is defined by a substantially
circumferential path around its defining sphere), or by radii that
lie in different planes intersecting the sphere (where path around
the defining sphere deviates from a circumferential path). The
segments thus resemble nearly, but not fully, completed circles
(circumferential path) or helical loops (non-circumferential path),
and they may be either of uniform or different diameters.
[0018] In any of the embodiments, the device is preferably formed
from a microcoil structure, but it may alternately be formed of a
flexible, filamentous, non-coil structure. Known non-coil
structures used in vaso-occlusive devices include, but are not
limited to, wires, slotted wires, spiral cut wires, tubes, slotted
tubes, spiral cut tubes, polymer filaments, polymer/metal composite
filaments, and micro-chains.
[0019] In any of the embodiments, the device, in its minimum energy
state secondary configuration, has a dimension that is
substantially larger (preferably at least about 25% greater) than
the largest dimension of the vascular space in which the device is
to be deployed. Most preferably, the length of the device, in its
minimum energy state secondary configuration, should be at least
about twice the maximum diameter of the targeted aneurysm or other
vascular site in which the device is to be installed. Also, it is
advantageous to provide in the device at least one curved segment
having a diameter, in the minimum energy state secondary
configuration, that is approximately equal to the largest diameter
of the targeted aneurysm or vascular site. Thus, when the device is
deployed inside a vascular site such as an aneurysm, the
confinement of the device within the site causes the device to
assume a three-dimensional configuration that has a higher energy
state than the minimum energy state. Because the minimum energy
state of the device is larger (in at least one dimension) than the
space in which it is deployed, the deployed device is constrained
by its intimate contact with the walls of the aneurysm from
returning to its minimum energy state configuration. Therefore, the
device still engages the surrounding aneurysm wall surface, thereby
minimizing shifting or tumbling due to blood flow dynamics.
Furthermore, the minimum energy state secondary configuration (to
which the device attempts to revert) is not one that is conducive
to "coin stacking", thereby minimizing the degree of compaction
that is experienced.
[0020] As will be better appreciated from the detailed description
that follows, the present invention provides for effective
embolization of vascular structures (particularly aneurysms) having
a wide variety of shapes and sizes. It is especially advantageous
for use in wide-necked aneurysms. Furthermore, as will be described
in more detail below, the present invention may be deployed using
conventional deployment mechanisms, such as microcatheters and
guidewires.
BRIEF DESCRIPTION OF THE DRAWINGS
[0021] FIG. 1 is a perspective view of a microcoil vaso-occlusive
device in accordance with a preferred embodiment of the present
invention;
[0022] FIG. 2 is a partial view of the device of FIG. 1, taken
within the area designated by the numeral 2 in FIG. 1;
[0023] FIGS. 3 and 4 are partial views of a microcoil
vaso-occlusive device in accordance with another form of the
preferred embodiment of the present invention;
[0024] FIG. 5 is a plan view of a microcoil vaso-occlusive device
in accordance with a first alternative embodiment of the
invention;
[0025] FIG. 6 is an elevational view of the present invention in
the process of being deployed through a microcatheter into a
wide-necked aneurysm;
[0026] FIG. 7 is a perspective view of a heat treatment fixture
used to manufacture the preferred embodiment of the present
invention;
[0027] FIG. 8 is a perspective view of a second alternative
embodiment of the invention;
[0028] FIG. 9 is an elevational view of the second alternative
embodiment of FIG. 8;
[0029] FIG. 10 is a plan view of another form of the first
alternative embodiment of the invention;
[0030] FIG. 11 is a plan view of a third alternative embodiment of
the invention;
[0031] FIGS. 12-15 are plan views of other forms of the preferred
embodiment of the invention;
[0032] FIG. 16 is a perspective view of a fourth alternative
embodiment of the invention, showing how its is formed on a
specialized heat treatment fixture, the latter being shown in a
simplified, idealized form; and
[0033] FIG. 17 is an elevational view of still another form of the
preferred embodiment of the present invention.
DETAILED DESCRIPTION OF THE INVENTION
[0034] Referring first to FIGS. 1-4 and 8, a microcoil
vaso-occlusive device 10, in accordance with a preferred embodiment
of the invention is shown. The device 10 comprises a suitable
length of wire formed into the primary configuration of a helical
microcoil 12 (FIG. 2). Suitable materials for the device 10 include
platinum, rhodium, palladium, rhenium, tungsten, gold, silver,
tantalum, and various alloys of these metals. Various surgical
grade stainless steels may also be used. Preferred materials
include the platinum/tungsten alloy known as Platinum 479 (92% Pt,
8% W, available from Sigmund Cohn, of Mount Vernon, N.Y.) and
titanium/nickel alloys (such as the titanium/nickel alloy known as
"nitinol"). Another material that may be advantageous is a
bimetallic wire comprising a highly elastic metal with a highly
radiopaque metal. Such a bimetallic wire would also be resistant to
permanent deformation. An example of such a bimetallic wire is a
product comprising a nitinol outer layer and an inner core of pure
reference grade platinum, available from Sigmund Cohn, of Mount
Vernon, N.Y., and Anomet Products, of Shrewsbury, Mass. Wire
diameters of about 0.0125 mm to about 0.150 mm may be used.
[0035] The microcoil 12 has a diameter that is typically in the
range of about 0.125 mm to about 0.625 mm, with a preferred a
preferred range, for most neurovascular applications, of about 0.25
mm to about 0.40 mm. The axial length of the microcoil 12 may be
anywhere from about 5 mm to about 1000 mm, with about 20 mm to
about 400 mm being typical.
[0036] The primary winding of the microcoil 12 is applied under
tension. The amount of tension, and the pitch of the primary
winding, determine the stiffness of the microcoil 12. These
parameters can be varied along the length of the microcoil 12 to
form a microcoil having different degrees of stiffness along its
length, which may be advantageous in certain applications.
[0037] The microcoil 12 is formed into a secondary configuration
that comprises a plurality of curved segments, each defining an
axis, whereby the microcoil 12 defines multiple axes. More
specifically, each of the curved segments defines a plane an axis
that is substantially perpendicular to the plane. In the preferred
embodiment of FIGS. 1-4, the curved segments are
tangentially-interconnected closed loops 14a, 14b that are
substantially circular, and that define a plurality of separate
axes 16. In one form of the preferred embodiment, shown in FIG. 1,
the loops 14a, 14b are substantially coplanar and define axes 16
that are substantially parallel. In another form of the preferred
embodiment, shown in FIGS. 3 and 4, each pair of adjacent loops
14a, 14b defines a shallow angle, whereby their respective axes 16
define an angle (.theta..sub.1, .theta..sub.2, .theta..sub.3, and
.theta..sub.4) of not more than about 90.degree. between them, and
preferably not more than about 45.degree..
[0038] The preferred embodiment of the invention typically includes
a pair of end loops 14a and at least one intermediate loop 14b.
Typically, there will be up to four intermediate loops 14b,
depending on the vascular site to be embolized, but there may be as
many as six or more, for use in very large vascular sites. The
intermediate loops are sized to have a diameter approximately equal
to the maximum diameter of the target vascular site (e.g., an
aneurysm), while the end loops 14a have a slightly smaller diameter
(preferably, approximately 1.5 mm smaller), for purposes to be
described below.
[0039] The primary microcoil 12 is formed into the secondary
configuration by heat treatment, as is well known in the art. For
example, the annealed primary coil may be initially placed into the
secondary configuration by winding or wrapping around a suitably
shaped and sized mandrel of refractory material, and then subjected
to an annealing temperature for a specified period of time. For
Platinum 479, for example, an annealing temperature of about
500.degree. C. to about 1000.degree. C., preferably approximately
670.degree. C., is maintained for about 30 to 90 minutes,
preferably about 60 minutes, then cooled to room temperature and
ultrasonically cleaned. The resultant secondary configuration is
thereby made permanent, and it becomes the minimum energy state
configuration of the microcoil 12.
[0040] FIG. 7 shows a heat treatment fixture 50 used in the
manufacture of the preferred embodiment of the invention. The
fixture 50 is made of a refractory material, and it includes a base
52 having a surface on which is provided a mandrel for the
secondary winding. The mandrel comprises a plurality of winding
pins 54a, 54b extending upwardly from the surface of the base 52.
The exemplary fixture 50 shown in the drawing has six pins arranged
in roughly a hexagonal pattern. There are two end winding pins 54a
adjacent each other, and four intermediate winding pins 54b. A pair
of fastening pegs 56 is located near one end of the fixture, for
fastening the ends of the primary coil 12.
[0041] The diameters of the end winding pins 54a are slightly
smaller than the diameters of the intermediate winding pins 54b to
achieve the size relationships described above. The spacings
between the pins 54a, 54b are only slightly greater than the
diameter of the primary coil 12, so that only one wind of the
primary coil can be passed around the pins with each winding of the
secondary coil. Each subsequent winding of the secondary coil is
thus stacked on top of the previous winding. This eliminates any
straight sections in the secondary coil, which, during deployment,
would tend to push the coil into the parent artery.
[0042] During the secondary winding process, the primary coil 12 is
kept under tension. The amount of tension can be adjusted to
control the degree of spring-back of the loops 14a, 14b of the
microcoil 12.
[0043] The secondary winding of the microcoil 12 is performed so
that the loops 14a, 14b reverse direction as the microcoil 12 is
wrapped around each successive pin on the fixture. This ensures
that loops will not coin stack, and that they will disperse
randomly throughout the aneurysm once deployed. Furthermore, in the
preferred embodiment, each loop is wound a complete 360.degree.
before the next loop is wound. This ensures that each loop will
completely seat within the aneurysm before the microcoil 12
reverses direction. With a complete loop intact, the loop strength
is maximized, and the loop distributes loads evenly.
[0044] FIGS. 12-15 and 17 illustrate alternative forms of the
above-described preferred embodiment. Specifically, in FIG. 12, a
microcoil 12' has a secondary configuration that includes a
plurality of connected curved segments, wherein the curved segments
are overlapping connected closed loops 14', that are substantially
circular, with each loop 14' defining a separate axis 16'. In FIG.
13, a microcoil 12'' has a secondary configuration that includes a
plurality of connected curved segments, wherein the curved segments
are tangentially-interconnected, substantially elliptical loops
14'', each defining a separate axis 16''. FIGS. 14 and 15 show
alternative forms that are similar to that of FIGS. 1-4, except
that the loops are of different diameters. Thus, in FIG. 14, a
microcoil 12''' has a secondary configuration that includes a
plurality of tangentially-interconnected, substantially circular
loops 14''' of progressively decreasing diameter, starting from a
loop 14'''c of the largest diameter, each of the loops defining a
unique axis 16'''. The variant form shown in FIG. 15 is similar to
that of FIG. 14, except that there is an additional small-diameter
loop 14'''d preceding the largest diameter loop 14'''c. A further
form of the preferred embodiment, illustrated in FIG. 17, comprises
a microcoil 12.sup.iv having a minimum energy state secondary
configuration in which a plurality of interconnected, tangential
loops 14.sup.iv are arranged so that each loop defines an axis
16.sup.iv that is orthogonal to a unique radius r of a circle, the
radii being separated by a fixed angle of arc .theta..
[0045] FIG. 5 shows a microcoil vaso-occlusion device 20 in
accordance with a first alternative embodiment of the invention.
This embodiment includes a primary microcoil 22 formed into a
secondary minimum energy state configuration that defines a
wave-form like structure comprising a longitudinal array of
laterally-alternating open loops 24 defining a plurality of
separate axes 26. As in the preferred embodiment, the alternative
embodiment may be in a first form in which the loops 24 are
substantially coplanar and their respective axes 26 are
substantially parallel, or in a second form in which each pair of
adjacent loops 24 defines a shallow angle, whereby their respective
axes 26 define an angle of not more than about 90.degree., and
preferably not more than about 45.degree., between them. The
materials, dimensions, and method of manufacture of this
alternative embodiment are, in all material respects, similar to
those of the preferred embodiment described above.
[0046] FIG. 10 illustrates a specific construction of this
embodiment, wherein the primary microcoil structure 22' is formed
into a secondary minimum energy state configuration having a
wave-form like structure that defines a substantially sinusoidal
waveform, defining a plurality of separate axes 26'. The waveform
has at least one maximum 22a and at least one minimum 22b, each of
which defines an arc of radius r, and wherein each arc is connected
to an adjacent arc by a straight section of length L, wherein L is
less than about 2r.
[0047] The method of using the present invention is shown in FIG.
6. In use, the proximal end of the microcoil 12 (or 22) is attached
to the distal end of an elongate delivery device, such as a
guidewire or microcatheter (not shown). The attachment may be by
any of a number of ways known in the art, as exemplified by the
following U.S. patents, the disclosures of which are expressly
incorporated herein by reference: U.S. Pat. No. 5,108,407--Geremia
et al.; U.S. Pat. No. 5,122,136--Guglielmi et al.; U.S. Pat. No.
5,234,437--Sepetka; U.S. Pat. No. 5,261,916--Engelson; U.S. Pat.
No. 5,304,195--Twyford, Jr. et al.; U.S. Pat. No.
5,312,415--Palermo; U.S. Pat. No. 5,423,829--Pham et al.; U.S. Pat.
No. 5,522,836--Palermo; U.S. Pat. No. 5,645,564--Northrup et al.;
U.S. Pat. No. 5,725,546--Samson; U.S. Pat. No. 5,800,453--Gia; U.S.
Pat. No. 5,814,062--Sepetka et al.; U.S. Pat. No. 5,911,737--Lee et
al.; U.S. Pat. No. 5,989,242--Saadat et al.; U.S. Pat. No.
6,022,369--Jacobsen et al. U.S. Pat. No. 6,063,100--Diaz et al.;
U.S. Pat. No. 6,068,644--Lulo et al.; and U.S. Pat. No.
6,102,933--Lee et al.
[0048] A target vascular site is visualized, by conventional means,
well-known in the art. The target vascular site may be an aneurysm
40 branching off a parent artery 42. The aneurysm 40 has a dome 44
connected to the branch artery by a neck 46. A catheter 30 is
passed intravascularly until it enters the dome 44 of the aneurysm
40 via the neck 46. The microcoil 12 is passed through the catheter
30 with the assistance of the guidewire or microcatheter until the
microcoil 12 enters the dome 44 of the aneurysm 40.
[0049] The undersized end loop 14a at the distal end of the
microcoil 12 enters the aneurysm first. This assists in seating the
first loop properly, because the smaller size keeps the first loop
inside the neck 46 of the aneurysm, avoiding the parent artery
42.
[0050] The intermediate loops 14b then enter the aneurysm. Because
they are sized to fit the aneurysm, they can deploy freely and
smoothly with minimal friction against the wall of the aneurysm.
Because the secondary configuration of the microcoil 12 is
essentially coplanar, all of the intermediate loops exert a force
against the walls of the aneurysm dome 44, thereby improving the
resistance of the microcoil 12 to shifting due to pulsatile blood
flow.
[0051] As the microcoil 12 enters the aneurysm, it attempts to
assume its secondary configuration. Because the microcoil, in its
secondary configuration, is larger than the aneurysm, however, it
is constrained into a deployed configuration in which it tends to
line the periphery of the aneurysm. In this deployed configuration,
the microcoil is in an energy state that is substantially higher
than its minimum energy state. Thus, when the device is deployed
inside a vascular site such as an aneurysm, the confinement of the
device within the site causes the device to assume a
three-dimensional configuration that has a higher energy state than
the minimum energy state. Because the minimum energy state of the
device is larger (in at least one dimension) than the space in
which it is deployed, the deployed device is constrained by its
intimate contact with the walls of the aneurysm from returning to
its minimum energy state configuration. Therefore, the device still
engages the surrounding aneurysm wall surface, thereby minimizing
shifting or tumbling due to blood flow dynamics. Furthermore, the
minimum energy state secondary configuration (to which the device
attempts to revert) is not one that is conducive to "coin
stacking", thereby minimizing the degree of compaction that is
experienced.
[0052] The undersized end loop 14a at the proximal end of the
microcoil 12 enters the aneurysm last. After the microcoil is fully
deployed, it is controllably detached from the delivery device by
any suitable means well-known in the art, thereby allowing the
delivery device to be withdrawn, leaving the microcoil in place to
embolize the aneurysm. After detachment, the proximal end loop 14a
curls into the neck 46 of the aneurysm 40, avoiding the parent
artery 42.
[0053] The microcoil is designed with a maximum loops diameter that
is dimensioned to line the periphery of the aneurysm upon
deployment, as mentioned above. For larger aneurysms, it is
advantageous to fill in a substantial portion of the interior
volume of the aneurysm by deploying one or more additional
microcoils, of progressively smaller maximum loop diameter.
[0054] FIGS. 8 and 9 illustrate a vaso-occlusion device in
accordance with a second alternative embodiment of the invention.
This embodiment includes a primary microcoil 60 formed into a
secondary minimum energy state configuration that forms a series of
tangential closed loops 62 (preferably substantially circular or
elliptical), wherein the entire structure subtends a first angle of
arc .theta..sub.1, and wherein each adjacent pair of circles or
ellipses defines a second angle of arc .theta..sub.2 between them.
Preferably, the first angle .theta..sub.1 is greater than about
30.degree., and the second angle .theta..sub.2 is less than about
half of the first angle .theta..sub.1. Although not illustrated in
the drawings, it will be appreciated that each loop 62 defines an
axis, whereby the angle formed between the axes of adjacent loops
62 is equal to .theta..sub.2.
[0055] FIG. 11 illustrates a vaso-occlusive device in accordance
with a third alternative embodiment of the invention. In this
embodiment, a microcoil 70 has a secondary configuration that forms
at least a pair of connected equiangular or logarithmic spirals 72,
each of the spirals defining an axis 73 that is orthogonal to the
plane defined by the spiral. For the purpose of this specification,
an equiangular or logarithmic spiral is defined as a curve that
cuts all radii vectors at a constant angle, where a radial vector R
is defined as a line drawn from any point P on the spiral to the
center of the spiral. Specifically, if the curve is a spiral, that
is, a curve having a radial vector R that is a monotonic increasing
function of the radial angle .theta., the spiral will be an
equiangular spiral if the angle a formed between a radial vector
and the tangent for any point P on the spiral is constant.
[0056] FIG. 16 illustrates a vaso-occlusive device in accordance
with a fourth alternative embodiment, wherein a microcoil 80 has a
secondary configuration that resembles a series of interconnected
complex curved segments 82, each of which is defined by a path
around the surface of a sphere 84. Each of the segments is thus
defined by a unique focus 86 located at the approximate center
point of the sphere 84 around which the path is generated, and by a
radius r extending from that locus 86 that is equal to the radius
of that sphere. Each segment may be defined by radii that are
coplanar (in the case of a segment that is defined by a
substantially circumferential path around its defining sphere), or
by radii that lie in different planes intersecting the sphere
(where path around the defining sphere deviates from a
circumferential path). The segments thus resemble nearly, but not
fully, completed circles (circumferential path) or helical loops
(non-circumferential path), and they may be either of uniform or
different diameters.
[0057] The present invention thus exhibits several advantages over
prior art three-dimensional microcoils. For example, there is
increased coverage of the aneurysm neck, due to the presence of
loops across the neck, yet the probability of any part of the
device intruding into the parent artery is reduced. The secondary
coil configuration also provides smoother deployment, and, once
deployed, the device exhibits greater resistance to coil
compaction, thereby increasing positional stability in the face of
pulsatile blood flow. This stability is achieved with lower overall
friction between the device and the aneurysm wall. Moreover, the
random distribution of loops throughout the aneurysm allows the
device to maintain a complex shape inside the aneurysm, yielding
improved embolization.
[0058] While a preferred embodiment and alternative embodiments of
the invention have been described herein, it will be appreciated
that a number of variations and modifications will suggest
themselves to those skilled in the pertinent arts. For example,
other secondary configurations than those described herein may be
found that will yield most, if not all, of the significant
advantages of the invention for treatment of the typical aneurysm,
or that will prove especially advantageous in specific clinical
applications. Also, for specific applications, the dimensions and
materials may be varied from those disclosed herein if found to be
advantageous. These and other variations and modifications are
considered to be within the spirit and scope of the invention, as
defined in the claims that follow.
* * * * *