U.S. patent application number 14/330456 was filed with the patent office on 2016-09-08 for closed tip dynamic microvalve protection device.
This patent application is currently assigned to SUREFIRE MEDICAL, INC.. The applicant listed for this patent is Surefire Medical, Inc.. Invention is credited to James E. Chomas, Bryan Pinchuk.
Application Number | 20160256626 14/330456 |
Document ID | / |
Family ID | 54196245 |
Filed Date | 2016-09-08 |
United States Patent
Application |
20160256626 |
Kind Code |
A9 |
Pinchuk; Bryan ; et
al. |
September 8, 2016 |
Closed Tip Dynamic Microvalve Protection Device
Abstract
An endovascular microvalve device for use in a vessel during a
therapy procedure includes an outer catheter, an inner catheter
displaceable within the outer catheter, and a filter valve coupled
to the distal ends of the inner and outer catheters. The valve is
constructed of a braid of elongate first filaments coupled together
at their proximal ends in a manner that the first filaments are
movable relative to each other along their lengths. A filter is
provided to the braid formed by electrostatically depositing or
spinning polymeric second filaments onto the braided first
filaments. The lumen of the inner catheter delivers a therapeutic
agent beyond the valve. The device is used to provide a therapy in
which a therapeutic agent is infused into an organ.
Inventors: |
Pinchuk; Bryan; (Denver,
CO) ; Chomas; James E.; (Denver, CO) |
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Applicant: |
Name |
City |
State |
Country |
Type |
Surefire Medical, Inc. |
Westminster |
CO |
US |
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Assignee: |
SUREFIRE MEDICAL, INC.
Westminster
CO
|
Prior
Publication: |
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Document Identifier |
Publication Date |
|
US 20150306311 A1 |
October 29, 2015 |
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|
Family ID: |
54196245 |
Appl. No.: |
14/330456 |
Filed: |
July 14, 2014 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
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14259293 |
Apr 23, 2014 |
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14330456 |
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61970202 |
Mar 25, 2014 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61F 2230/0089 20130101;
A61F 2/013 20130101; A61F 2230/0071 20130101; A61M 2005/1655
20130101; A61F 2230/0067 20130101; A61M 5/165 20130101; A61F
2230/0076 20130101; A61F 2002/016 20130101; A61F 2/011 20200501;
A61M 5/16881 20130101; A61F 2250/0098 20130101; A61F 2230/0078
20130101 |
International
Class: |
A61M 5/168 20060101
A61M005/168; A61M 5/165 20060101 A61M005/165 |
Claims
1. An endovascular microvalve device for temporary use in a vessel
having a vessel wall during an intravascular procedure, comprising:
a) a flexible outer catheter having a proximal end and a distal
end; b) a flexible inner catheter having a proximal end and a
distal end with an orifice, the inner catheter extending through
and longitudinally displaceable relative to the outer catheter; and
c) a filter valve having a proximal end and distal end, the
proximal end of the filter valve coupled to the distal end of the
outer catheter, and the distal end of the filter valve coupled to
the inner catheter adjacent the distal end of the inner catheter,
such that longitudinal displacement of the inner catheter relative
to the outer catheter moves the filter valve from a non-deployed
configuration to a deployed configuration, the filter valve having
a proximal portion comprising a braided filamentary structure and
distal portion comprising a non-braided spirally wound filamentary
structure, and the distal portion further comprising a porous
polymeric material coupled to the spiral wound filamentary
structure, the porous polymeric material defining a pore size not
exceeding 500 .mu.m.
2. An endovascular microvalve device according to claim 1, wherein:
once the filter valve is in the deployed state in the vessel, the
filter valve is dynamically movable depending on a local fluid
pressure about the filter valve, such that, when the fluid pressure
is higher on a proximal side of the filter valve, the filter valve
assumes a configuration with a first diameter smaller than the
diameter of the vessel such that fluid flow about the filter valve
is permitted, and when the fluid pressure is higher on a distal
side of the filter valve, the filter valve assumes a configuration
with a second diameter relatively larger than the first diameter
and in which the filter valve is adapted to contact the vessel
wall.
3. An endovascular microvalve device according to claim 1, wherein:
the proximal portion exerts a higher radial force than the distal
portion of the filter valve.
4. An endovascular microvalve device according to claim 1, wherein:
the filter valve defines a maximum diameter at an intersection of
the proximal and distal portions.
5. An endovascular microvalve device according to claim 1, wherein:
the braided filamentary structure of the proximal portion comprises
a first number of filaments, and the non-braided spirally wound
filaments of the distal portion comprises a second number of
filaments, and the first number is greater than the second
number.
6. An endovascular microvalve device according to claim 1, wherein:
the spirally wound filamentary structure consists essentially of
filaments extending in a common rotational direction.
7. An endovascular microvalve device according to claim 1, wherein:
the spirally wound filamentary structure includes filaments
extending in both clockwise and counter-clockwise rotational
directions.
8. An endovascular microvalve device according to claim 1, wherein:
the spirally wound filamentary structure consists essentially of
filaments that are equally displaced about a circumference of the
filter valve.
9. An endovascular microvalve device according to claim 1, wherein:
the spirally wound filamentary structure includes spiral wound
filaments that are unequally displaced about a circumference of the
filter valve.
10. An endovascular microvalve device according to claim 1,
wherein: the braided filamentary structure in the proximal portion
and spirally wound filamentary structure of the distal portion are
comprised of filaments having a diameter of 0.025 mm to 0.127
mm.
11. An endovascular microvalve device according to claim 10,
wherein: the filaments of the proximal portion have proximal ends
secured relative to each other on the outer catheter such that the
filaments of the proximal portion define a round configuration
extending between their secured proximal ends on the outer catheter
and the distal portion of the filter valve.
12. An endovascular microvalve device according to claim 1,
wherein: the spirally wound filamentary structure includes spirally
wound filaments, and the filaments extends in a first winding
direction when the filter valve is in the non-deployed
configuration, and when the filter valve is moved from the
non-deployed configuration to the deployed configuration, the
filaments reverse winding direction relative to the first winding
direction.
13. An endovascular microvalve device according to claim 1,
wherein: the proximal portion further includes a porous polymeric
material provided to the braided filamentary structure.
14. An endovascular microvalve device according to claim 1,
wherein: the filter valve in the deployed configuration forms a
substantially oblong spherical or frustoconical shape.
15. An endovascular microvalve device according to claim 1,
wherein: in a non-deployed configuration, the filter valve includes
a distal face that is convex in shape, and in a deployed
configuration, the distal face of the filter valve is planar or
concave.
16. An endovascular microvalve device for temporary use in a vessel
having a vessel wall during an intravascular procedure, comprising:
a) a flexible outer catheter having a proximal end and a distal
end; b) a flexible inner catheter having a proximal end and a
distal end with an orifice, the inner catheter extending through
and longitudinally displaceable relative to the outer catheter; and
c) a filter valve having a proximal end and distal end, the
proximal end of the filter valve coupled to the distal end of the
outer catheter, and the distal end of the filter valve coupled to
the inner catheter adjacent the distal end of the inner catheter,
such that longitudinal displacement of the inner catheter relative
to the outer catheter moves the filter valve from a non-deployed
configuration to a deployed configuration, the filter valve having
a proximal portion comprising a braided filamentary structure
consisting of a first number of filamentary portions, and distal
portion comprising an arrangement of second number of filamentary
portions, the second number fewer than the first number, and the
distal portion further comprising a porous polymeric material
coupled to the filamentary portions of the distal portion, the
porous polymeric material defining a pore size not exceeding 500
.mu.m.
17. An endovascular microvalve device according to claim 16,
wherein: once the filter valve is in the deployed state in the
vessel, the filter valve is dynamically movable depending on a
local fluid pressure about the filter valve, such that, when the
fluid pressure is higher on a proximal side of the filter valve,
the filter valve assumes a configuration with a first diameter
smaller than the diameter of the vessel such that fluid flow about
the filter valve is permitted, and when the fluid pressure is
higher on a distal side of the filter valve, the filter valve
assumes a configuration with a second diameter relatively larger
than the first diameter and in which the filter valve is adapted to
contact the vessel wall.
18. An endovascular microvalve device according to claim 16,
wherein: the proximal portion exerts a higher radial force than the
distal portion of the filter valve.
19. An endovascular microvalve device according to claim 16,
wherein: the second filamentary portions coextend from the first
filamentary portions.
20. An endovascular microvalve device according to claim 16,
wherein: the first and second filamentary portions are discrete
from each other.
21. An endovascular microvalve device according to claim 16,
wherein: the second filamentary portions are equally displaced
about a circumference of the filter valve.
22. An endovascular microvalve device according to claim 16,
wherein: the second filamentary portions are unequally displaced
about a circumference of the filter valve.
23. An endovascular microvalve device according to claim 16,
wherein: the second filamentary portions are spirally wound about
the distal portion.
24. An endovascular microvalve device according to claim 23,
wherein: the second filamentary portions extends in a first winding
direction when the filter valve is in the non-deployed
configuration, and when the filter valve is moved from the
non-deployed configuration to the deployed configuration, the
second filamentary portions reverse winding direction relative to
the first winding direction.
25. An endovascular microvalve device according to claim 16,
wherein: the first and second filamentary portions have a diameter
of 0.025 mm to 0.127 mm.
26. An endovascular microvalve device according to claim 25,
wherein: the first filamentary portions of the proximal portion
have proximal ends secured relative to each other on the outer
catheter such that the first filamentary portions define a round
configuration extending between their secured proximal ends on the
outer catheter and the distal portion of the filter valve.
27. An endovascular microvalve device according to claim 16,
wherein: the filter valve defines a maximum diameter at an
intersection of the proximal and distal portions.
28. An endovascular microvalve device according to claim 16,
wherein: the proximal portion further includes a porous polymeric
material provided to the braided filamentary structure.
29. An endovascular microvalve device according to claim 16,
wherein: in a non-deployed configuration, the filter valve includes
a distal face that is convex in shape, and in a deployed
configuration, the distal face of the filter valve is planar or
concave.
30. A method of a using a microvalve device, comprising: a)
advancing a microvalve device to a target location, the microvalve
device having i) a flexible outer catheter having a proximal end
and a distal end, ii) a flexible inner catheter having a proximal
end and a distal end with an orifice, the inner catheter extending
through and longitudinally displaceable relative to the outer
catheter, and iii) a filter valve having a proximal end and distal
end, the proximal end of the filter valve coupled to the distal end
of the outer catheter, and the distal end of the filter valve
coupled to the inner catheter adjacent the distal end of the inner
catheter, such that longitudinal displacement of the inner catheter
relative to the outer catheter moves the filter valve from a
non-deployed configuration to a deployed configuration, the filter
valve having a proximal portion comprising a braided filamentary
structure; b) infusing a therapeutic agent through the inner
catheter and out of the distal end of the inner catheter; c)
retracting the inner catheter relative to the outer catheter to
invert at least a portion of the filter valve into the outer
catheter; and d) withdrawing the microvalve device from the target
location.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation-in-part of U.S. Ser. No.
14/259,293, filed Apr. 23, 2014, which is hereby incorporated by
reference herein in its entirety.
[0002] This application is related to U.S. Pat. No. 8,500,775 and
U.S. Pat. No. 8,696,698, which are hereby incorporated by reference
herein in their entireties.
BACKGROUND OF THE INVENTION
[0003] 1. Field of Invention
[0004] The present invention relates generally to a valve for
performing a medical embolizing treatment, and particularly to a
valve that increases penetration of a treatment agent into targeted
blood vessels and reduces reflux of the treatment agent into
non-targeted vessels.
[0005] 2. State of the Art
[0006] Embolization, chemo-embolization, and radio-embolization
therapy are often clinically used to treat a range of diseases,
such as hypervascular liver tumors, uterine fibroids, secondary
cancer metastasis in the liver, pre-operative treatment of
hypervascular menangiomas in the brain and bronchial artery
embolization for hemoptysis. An embolizing agent may be embodied in
different forms, such as beads, liquid, foam, or glue placed into
an arterial vasculature. The beads may be uncoated or coated. Where
the beads are coated, the coating may be a chemotherapy agent, a
radiation agent or other therapeutic agent. When it is desirable to
embolize a small blood vessel, small bead sizes (e.g., 10 .mu.m-100
.mu.m) are utilized. When a larger vessel is to be embolized, a
larger bead size (e.g., 100 .mu.m-900 .mu.m) is typically
chosen.
[0007] While embolizing agent therapies which are considered
minimally or limited invasive have often provided good results,
they have a small incidence of non-targeted embolization which can
lead to adverse events and morbidity. Infusion with an infusion
microcatheter allows bi-directional flow. That is, the use of a
microcatheter to infuse an embolic agent allows blood and the
infused embolic agent to move forward in addition to allowing blood
and the embolic agent to be pushed backward (reflux). Reflux of a
therapeutic agent causes non-target damage to surrounding healthy
organs. In interventional oncology embolization procedures, the
goal is to bombard a cancer tumor with either radiation or
chemotherapy. It is important to maintain forward flow throughout
the entire vascular tree in the target organ in order to deliver
therapies into the distal vasculature, where the therapy can be
most effective. This issue is amplified in hypovascular tumors or
in patients who have undergone chemotherapy, where slow flow limits
the dose of therapeutic agent delivered and reflux of agents to
non-target tissue can happen well before the physician has
delivered the desired dose.
[0008] The pressure in a vessel at multiple locations in the
vascular tree changes during an embolic infusion procedure.
Initially, the pressure is high proximally, and decreases over the
length of the vessel. Forward flow of therapy occurs when there is
a pressure drop. If there is no pressure drop over a length of
vessel, therapy does not flow downstream. If there is a higher
pressure at one location, such as at the orifice of a catheter, the
embolic therapy flows in a direction toward lower pressure. If the
pressure generated at the orifice of an infusion catheter is larger
than the pressure in the vessel proximal to the catheter orifice,
some portion of the infused embolic therapy travels up stream
(reflux) into non-target vessels and non-target organs. This
phenomenon can happen even in vessels with strong forward flow if
the infusion pressure (pressure at the orifice of the catheter) is
sufficiently high.
[0009] During an embolization procedure, the embolic agents clog
distal vessels and block drainage of fluid into the capillary
system. This leads to an increase in the pressure in the distal
vasculature. With the increased pressure, there is a decrease in
the pressure gradient and therefore flow slows or stops in the
distal vasculature. Later in the embolization procedure, larger
vessels become embolized and the pressure increases proximally
until there is a system that effectively has constant pressure
throughout the system. The effect is slow flow even in the larger
vessels, and distally the embolic agent no longer advances into the
target (tumor).
[0010] In current clinical practice with an infusion catheter, the
physician attempts to infuse embolics with pressure that does not
cause reflux. In doing this, the physician slows the infusion rate
(and infusion pressure) or stops the infusion completely. The
clinical impact of current infusion catheters and techniques is two
fold: low doses of the therapeutic embolic is delivered and there
is poor distal penetration into the target vessels.
[0011] Additionally, reflux can be a time-sensitive phenomenon.
Sometimes, reflux occurs as a response to an injection of the
embolic agent, where the reflux occurs rapidly (e.g., in the
time-scale of milliseconds) in a manner which is too fast for a
human operator to respond. Also, reflux can happen momentarily,
followed by a temporary resumption of forward flow in the blood
vessel, only to be followed by additional reflux.
[0012] FIG. 1 shows a conventional (prior art) embolization
treatment in the hepatic artery 106. Catheter 101 delivers
embolization agents (beads) 102 in a hepatic artery 106, with a
goal of embolizing a target organ 103. It is important that the
forward flow (direction arrow 107) of blood is maintained during an
infusion of embolization agents 102 because the forward flow is
used to carry embolization agents 102 deep into the vascular bed of
target organ 103.
[0013] Embolization agents 102 are continuously injected until
reflux of contrast agent is visualized in the distal area of the
hepatic artery. Generally, since embolization agents 102 can rarely
be visualized directly, a contrast agent may be added to
embolization agents 102. The addition of the contrast agent allows
for a visualization of the reflux of the contrast agent (shown by
arrow 108), which is indicative of the reflux of embolization
agents 102. The reflux may, undesirably, cause embolization agents
102 to be delivered into a collateral artery 105, which is proximal
to the tip of catheter 101. The presence of embolization agents 102
in collateral artery 105 leads to non-target embolization in a
non-target organ 104, which may be the other lobe of the liver, the
stomach, small intestine, pancreas, gall bladder, or other
organ.
[0014] Non-targeted delivery of the embolic agent may have
significant unwanted effects on the human body. For example, in
liver treatment, non-targeted delivery of the embolic agent may
have undesirable impacts on other organs including the stomach and
small intestine. In uterine fibroid treatment, the non-targeted
delivery of the embolic agent may embolize one or both ovaries
leading to loss of menstrual cycle, subtle ovarian damage that may
reduce fertility, early onset of menopause and in some cases
substantial damage to the ovaries. Other unintended adverse events
include unilateral deep buttock pain, buttock necrosis, and uterine
necrosis.
[0015] Often, interventional radiologists try to reduce the amount
and impact of reflux by slowly releasing the embolizing agent
and/or by delivering a reduced dosage. The added time, complexity,
increased x-ray dose to the patient and physician (longer
monitoring of the patient) and potential for reduced efficacy make
the slow delivery of embolization agents suboptimal. Also, reducing
the dosage often leads to the need for multiple follow-up
treatments. Even when the physician tries to reduce the amount of
reflux, the local flow conditions at the tip of the catheter change
too fast to be controlled by the physician, and therefore rapid
momentary reflux conditions can happen throughout infusion.
[0016] U.S. Pat. No. 8,696,698, previously incorporated herein,
describes a microvalve infusion system for infusing an embolic
agent to a treatment site in a manner that overcomes many of the
issues previously identified with infusion using an infusion
catheter alone. Referring to prior art FIGS. 2A and 2B, the
microvalve infusion system 200 includes a dynamically adjustably
filter valve 202 coupled to the distal end of a delivery catheter
204. The delivery catheter and filter valve extend within an outer
catheter 206. The filter valve 202 is naturally spring biased by
its construction of filamentary elements 208 to automatically
partially expand within a vessel when it is deployed from the outer
catheter 206, and is coated with a polymer coating 210 that has a
pore size suitable to filter an embolic therapeutic agent. More
particularly, the filter valve 202 has an open distal end 212 and
is coupled relative to the delivery catheter 204 such that an
embolic agent infused through the delivery catheter 204 and out of
the distal orifice 214 of the delivery catheter 204 exits within
the interior 216 of the filter valve. In view of this construction,
upon infusion, an increase in fluid pressure results within the
filter valve and causes the filter valve 202 to open, extend across
a vessel, and thereby prevent reflux of the infused embolic agent.
In addition, as the fluid is pressurized through the delivery
catheter and into the filter valve, the downstream pressure in the
vessel is increased which facilitates maximum uptake into the
target tissue for therapeutically delivered agents. Further, the
filter valve is responsive to local pressure about the valve which
thereby enables substantially unrestricted forward flow of blood in
the vessel, and reduces or stops reflux (regurgitation or backward
flow) of embolization agents which are introduced into the
blood.
[0017] However, the devices in U.S. Pat. No. 8,696,698 have certain
issues that may not always be advantageous. In various disclosed
FIG. 44, the devices shown have a large distal diameter which
limits trackability in tortuous branching vasculature. The distal
end of the device in a collapsed, undeployed state is defined by
the size of an outer catheter 206, which can be significantly
larger than the outer diameter delivery catheter 204 that supports
the filter valve 202 and significantly larger than the outer
diameter of a guidewire (not shown) used to the guide the
microvalve to the target location within the vessel. As such,
tracking the filter valve into the smaller vascular branches does
not have a desired reliability. In addition, once the device is
tracked to a treatment location, deployment of the filter valve
requires that the frictional force between the filter valve and the
outer catheter be overcome. Overcoming such forces can potentially
abrade the polymer coating on the filter valve. Improvements to
such designs was provided in other figures disclosed in U.S. Pat.
No. 8,696,698, so that the outer diameter of the distal aspect of
the device is reduced in size to in a manner that would faciliate
tracking. However, once any of the embodiments of filter valve 202
in U.S. Pat. No. 8,696,698 are shown in the open configuration,
they assumes the shape of an open frustocone, which allows
refluxing therapeutic embolic agent to enter the valve. This may
lead to therapeutic agent remaining in the filter valve,
particularly under conditions of slow forward flow within the
vessel, which potentially could result in incomplete dosing.
SUMMARY OF THE INVENTION
[0018] An infusion device is provided that includes an outer
catheter, and inner infusion catheter extending through the outer
catheter, and a dynamically adjustable filter valve coupled to both
of the outer and inner catheters. The filter valve is formed from a
naturally spring-biased filamentary construction that is biased to
radially expand and has a proximal end and a distal end. The
proximal end of the filter valve is coupled to a distal end of the
outer catheter, and the distal end of the filter valve is coupled
to a distal end of the inner catheter. The filter valve has a
closed filtering distal portion, with the proximal and distal
portions of the valve separate by the circumference about the
maximum diameter of the filter valve. The inner infusion catheter
is configured to deliver a therapeutic embolic agent distal of the
closed distal portion of the filter valve.
[0019] The filter valve can be manually displaced between open and
closed configurations by longitudinally displacing the distal end
of the inner catheter relative to the distal end of the outer
catheter. By displacing the inner catheter distally relative to the
outer catheter, the filter valve is moved into a collapsed
configuration, suitable for delivery to the treatment site. In the
collapsed configuration, the tip is tapered and assumes a form that
has excellent trackability over a guidewire to be advanced to a
treatment site. To deploy the filter valve, the inner catheter is
retracted relative to the outer catheter to cause the filter valve
to reconfigure, resulting in radial expansion toward a vessel wall.
In addition, the spring-bias of the valve also operates to radial
expand the filter valve, paricularly when subject to a pressure
differential on opposing sides of the filter valve. In a preferred
aspect of the invention, the proximal portion of the filter valve
has a different radial expansion force than the distal portion of
the filter valve. More preferably, the proximal portion has a
substantially greater radial expansion force than the distal
portion. Once the filter valve is in a deployed open configuration,
i.e., with the distal tip in a retracted position relative to the
delivery position, the filter valve is dynamically responsive to
local pressure about the filter valve. Under the dynamically
responsive operation, substantially unrestricted forward flow of
blood in the vessel is permitted, while backflow is prevented to
stop reflux of the therapeutic agent within the vessel.
[0020] Upon retrieval of the infusion device at the end of the
procedure the inner catheter can be further retracted into the
outer catheter (such that the filter valve is substantially
inverted and received within the outer catheter) to thereby capture
and contain any therapeutic agent remaining on the filter
valve.
BRIEF DESCRIPTION OF DRAWINGS
[0021] Prior art FIG. 1 shows a conventional embolizing catheter in
a hepatic artery with embolizing agent refluxing into a
non-targeted organ.
[0022] Prior art FIGS. 2A and 2B are schematic figures of a prior
art filter valve device shown in an undeployed configuration and a
deployed configuration, respectively.
[0023] FIGS. 3A and 3B are schematic figures of an exemplary
embodiment of a therapeutic filter valve device in a deployed state
and an undeployed state, respectively.
[0024] FIG. 4 is a schematic view of a shape of the distal end of a
deployed filter valve device.
[0025] FIG. 5 is a schematic view of another shape of the distal
end of a deployed filter valve device.
[0026] FIG. 6A-6D are broken schematic diagrams of the exemplary
embodiment of the filter valve device of FIGS. 3A and 3B, in use,
with the distal end of the device illustrated positioned within a
vessel.
[0027] FIG. 7 is perspective distal end photographic view of the
distal end of the filter valve device in a deployed
configuration.
[0028] FIGS. 8A-8C are schematic views of the distal end of the
filter valve device in non-deployed and deployed configurations,
indicating the respective positions of radio-opaque marker
bands.
[0029] FIG. 9 is a graph indicating the variable pressure control
distal of the filter valve device.
[0030] FIGS. 10A-10C are schematic views of the deployed filter
valve device, using variable pressure control to selectively infuse
primary and branch vessels.
[0031] FIG. 11 is a schematic distal end view of an alternate
coating construct for the filter valve device.
[0032] FIG. 12 is a schematic distal end view of another coating
construct for the filter valve device.
[0033] FIG. 13 is a schematic distal end view of yet another
alternate coating construct for the filter valve device.
[0034] FIG. 14 is a schematic distal end view of a braid angle
construct for any of the filter valve devices.
[0035] FIG. 15 is a schematic distal end view of another construct
of for a filter valve device.
[0036] FIG. 16 is a schematic distal end view of yet another
construct for a filter valve device.
[0037] FIGS. 17A-17C are schematic views of the distal end of still
yet another construct for a filter valve device in non-deployed,
partially deployed, and fully deployed configurations.
[0038] FIG. 18 is a distal end view of the filter valve device of
FIGS. 17A-17C, illustrating one arrangement for the wire filaments
in the distal portion of the filter valve.
[0039] FIG. 19 is a distal end view of a filter valve device,
showing an alternate arrangement for the wire filaments in the
distal portion of the filter valve.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0040] With reference to the human body and components of the
devices and systems described herein which are intended to be
hand-operated by a user, the terms "proximal" and "distal" are
defined in reference to the user's hand, with the term "proximal"
being closer to the user's hand, and the term "distal" being
further from the user's hand, unless alternate definitions are
specifically provided.
[0041] A first exemplary embodiment of a microvalve device 300
according to the invention is seen in FIGS. 3A and 3B. It is noted
that respective portions of the system illustrated in FIGS. 3A and
3B are not shown proportional to their intended size, but rather
that the distal portion is illustrated significantly enlarged for
purposes of explanation. As shown in FIG. 3A, the device 300
includes a flexible outer catheter 302 having a proximal end 304
and a distal end 306, a flexible inner delivery catheter 308
extending through and longituidnally displaceable relative to the
outer catheter 304 and having a proximal end 310 and a distal end
312, and a filter valve 314 coupled to the distal ends 306, 312 of
the outer and inner catheters 304, 308. The proximal end 310 of the
inner catheter is preferably mounted to a hub 316 with a rigid
tubular coupling member 318. The tubular coupling member 318 is
preferably a stainless steel hypotube or similar structure. An
infusion lumen 320 is defined from the hub 316 through to the
distal end 312 of the inner catheter and is adapted for delivery of
a therpeutic agent, incuding an embolizing agent, from outside the
body of the patient (not shown) to a target vessel (artery or vein)
in the patient. The proximal end 304 of the outer catheter 302
preferably includes a side arm port 322 that is in fluid
communication with an annular space 324 formed between the inner
and outer catheters 304, 308 and extending into the interior of the
filter valve 314, and to flush the annular space 324 of the filter
valve. Flushing such space, such as with a lucribant, including
saline, operates to reduce friction between the inner and outer
catheter to faciliate longituidnal movement therebetween.
[0042] A first radio-opaque marker band 326 is provided at the
distal end 312 of the inner catheter 308, and a second preferably
larger radio-opaque marker band 328 is provided at the distal end
306 of the outer catheter 302. A third radio-opaque marker band 330
is provided to the inner catheter 308 in a defined positional
relationship relative to the second marker band 328. By example,
the third marker band 330 may be co-longitudinally positioned with
the second marker band 328 when the inner and outer catheters 302,
308 are positioned to cause the filter valve 314 to be in a
deployed configuration, as shown in FIG. 3A and disucssed below.
FIG. 3B illustrates the microvalve device 300 in a non-deployed
configuration and relative positioning of the three marker bands
326, 328, 330. During use of the device 300, the in vivo relative
positions of the marker bands 326, 328, 330, viewed
fluroscopically, indicates the displacement of the distal ends 306,
312 of the inner and outer catheters and the consequent
configuration of the filter valve, as discussed in more detail
below.
[0043] A handle 332 is optionally provided at or adjacent the
proximal ends of the inner and outer catheters 302, 308 (including
tubular coupling member 318) to controllably longitudially displace
the inner and outer catheters relative to each other. By way of
example only, the handle 322 may include a standard slider
assembly, e.g., in the form of a spool and shaft, that converts
manual longitudinal movement of the user into a desired and
controlled longitudinal displacement between the inner and outer
catheters. As yet another alternative, the handle may include a
rotation knob 334 connected to a lead screw that converts manual
user rotational movement into a desired and controlled longitudinal
displacement between the distal ends of the inner and outer
catheters, such as shown by arrow 336 (FIG. 3B).
[0044] The inner catheter 308 is between two and eight feet long,
and has an outer diameter of between 0.67 mm and 3 mm
(corresponding to catheter sizes 2 French to 9 French), and is made
from a liner made of fluorinated polymer such as
polytetrafluoroethylene (PTFE) or fluorinated ethylene propylene
(FEP), a braid made of metal such as stainless steel or titanium,
or a polymer such as polyethylene terephthalate (PET) or liquid
crystal polymer, and an outer coating made of a polyether block
amide thermoplastic elastomeric resin such as PEBAX.RTM.,
polyurethane, polyamide, copolymers of polyamide, polyester,
copolymers of polyester, fluorinated polymers, such as PTFE, FEP,
polyimides, polycarbonate or any other suitable material, or any
other standard or specialty material used in making catheters used
in the bloodstream.
[0045] The outer catheter 302 is comprised of polyurethane,
polyamide, copolymers of polyamide, polyester, copolymers of
polyester, fluorinated polymers, such as PTFE, FEP, polyimides,
polycarbonate or any other suitable material. The outer catheter
302 may also contain a braid composed of metal such as stainless
steel or titanium, or a polymer such as PET or liquid crystal
polymer, or any other suitable material. The wall thickness of the
outer catheter 302 is preferably in the range of 0.05 mm to 0.25 mm
with a more preferred thickness of 0.1 mm-0.15 mm.
[0046] The distal end 340 of the filter valve 314 is fused or
otherwise fixedly coupled (both longituidnally and rotationally
fixed) adjacent, but preferably slightly proximally displaced from,
the distal end 312 of the inner catheter 308, and the proximal end
342 of the filter valve is fused or otherwise coupled at or
adjacent the distal end 306 of the outer catheter 302.
[0047] The filter valve 314 is composed of one, two, or more metal
(e.g., stainless steel or Nitinol) or polymer filaments 350, which
form a substantially closed shape when deployed and not subject to
outside forces. Where polymeric filaments are utilized, the
filaments 350 may be composed of PET, polyethylene-napthalate
(PEN), liquid crystal polymer, fluorinated polymers, nylon,
polyamide or any other suitable polymer. If desired, when polymeric
filaments are utilized, one or more metal filaments may be utilized
in conjunction with the polymeric filaments. According to one
aspect of the invention, where a metal filament is utilized, it may
be of radio-opaque material to facilitate tracking the filter valve
314 and its configuration within the body. In a deployed, expanded
diameter configuration, the filter valve 314 is capable of being
modified in shape by fluid forces. It is preferred that the
filaments 350 not be bonded to each between their ends so to enable
the valve to rapidly automatically open and close in response to
dynamic flow conditions. The multiple filaments 350 of the filter
valve are preferably braided and can move relative to each other
between their ends. As discussed hereinafter, the filaments are
spring biased (i.e., they have "shape memory") to assume a desired
crossing angle relative to each other so that the valve can
self-assume a desired shape.
[0048] In the device shown in FIG. 3A, the assumed shape in
substantially spherical, though as described hereinafter the shape
can be substantially frustoconical. (For purposes herein the term
"substantially spherical" should be understood to include not only
a sphere, but a generally rounded shape including a spherical
portion or a rounded oblong shape 314a, such as shown in FIG. 4, or
a portion thereof. For purposes herein the term "substantially
frustoconical" should be understood to include not only a generally
truncated cone, but a truncated hyperboloid, a truncated
paraboloid, and any other shape 314b which starts from a circular
proximal end 342b at the distal end 306 of the outer catheter 302
and diverges therefrom and returns to close back down at the distal
end 340b of the filter valve adjacent the distal end 312 of the
inner catheter 308, as shown in FIG. 5). In all embodiments, the
shape of the filter valve 314 is closed down at or adjacent the
respective ends 306, 312 of the outer and inner catheters 302, 308,
and can be defined by a proximal hemispherical portion 346 and a
distal hemispherical portion 348, or two conical portions, or a
proximal spherical portion and a distal conical portion, or a
proximal conical portion and a distal spherical portion, or any of
the preceding with an intervening shaped portion therebetween,
which are joined together at preferably the largest diameter ends
of the respective portions. As such, it is appreciated that the
proximal and distal portions 346, 348 of the filter valve 314 are
not required to be longitudinally symmetrical, and may be
asymmetrical, in construction, which is apparent in the
non-deployed configuration of the filter valve 314 shown in FIG.
3B. The joined proximal and distal portions each may have filaments
oriented at a different braid angle, discussed below. In addition,
the proximal and distal portions may be joined mechanically via the
ends of the filaments, or by the filter material, which is
discussed in more detail below.
[0049] The filter valve 314 is designed to be manually reconfigured
between non-deployed and deployed configurations by movement of the
inner and outer catheters relative to each other, wherein in each
of the non-deployed and deployed configurations the distal end of
the filter valve extends outside and distally of the distal end of
the outer catheter. As shown in FIGS. 3B and 6A, in the
non-deployed configuration, the filter valve 314 is provided with a
smaller maximum diameter suitable for tracking the device over a
guidewire 360 (FIG. 6A) through the vessels 362 to a treatment
site. The inner catheter 308 is displaced distally relatively to
the outer catheter 302 (in the direction of arrow 380) to stretch
or otherwise present the filter valve in an elongate configuration
having a tapered tip which facilitates trackability over the
guidewire 360. In this collapsed, non-deployed configuration, the
inner catheter 308 is preferably pushed as distal as possible
relative to the outer catheter 302. In a preferred embodiment, the
non-deployed elongated configuration of the filter valve tapers
distally over at least 50%, and preferably at least 75%, of its
length.
[0050] Then, referring to FIG. 6B, once the filter valve is
positioned at the treatment site in the vessel 362, the inner
catheter 308 can be retracted relative to the outer catheter 302
(in the direction of arrow 382) to expand the filter valve 314 and
cause the filter valve to assume (initially) a partially deployed
configuration within the vessel in which the filter valve does not
seal against the vessel wall 362. Alternatively or thereafter, as
shown in FIG. 6C, the inner catheter 308 can be further refracted
relative to the outer catheter 302 (as indicated by arrow 384) to
more fully expand the filter valve 314 to seal against the vessel
wall 362. This configuration of the filter valve 314 is also shown
in FIG. 7. When retracted into the configuration shown in FIG. 6B,
the proximal end of the filter valve 314 forms a distal facing
plane or concave surface 368 (with it being understood that in the
non-deployed configuration of the filter valve presents a distal
facing convex or convexly conical surface), while the proximal
facing surface remains unmodified in shape and is generally a
smooth convex surface. Then, with the filter valve deployed,
embolization agents 388 are delivered under pressure distally
through and out of the inner catheter, distal of the filter valve,
and into the vessel. Delivery of the embolization agents in this
manner will result in a downstream pressure change that initially
causes higher pressure distal of the filter valve than upstream of
the filter valve rapidly sealing to the vessel wall and directing
all infusion pressure downstream. In its open position, the filter
valve stops embolization agents from traveling upstream past the
filter valve in a proximal `reflux` direction. In addition, because
the filter valve is a closed shape and delivers the embolic distal
of the filter valve, 100% of the dose delivered is provided to the
patient; i.e., without the potential for any of the dose to remain
within the filter valve. Further, the shape of the proximal surface
of the deployed filter valve presents reduced resistance to blood
passing the filter valve in the downstream direction, but presents
a distal facing surface at a different orientation and one that is
substantially perpendicular to the vessel wall and has significant
resistance to flow in the upstream direction so as to prevent
reflux.
[0051] Turning now to FIGS. 8A-8C, the above described radio-opaque
first, second and third marker bands 326, 328, 330 facilitate
determining the in vivo configuration of the filter valve.
Referring to FIG. 8A, by way of example only, when the three marker
bands 326, 328, 330 are shown spaced apart, the filter valve 314
can be indicated to be in the non-deployed configuration. In FIG.
8B, with the third marker band 330 offset substantially closer to
the second marker band 328, the filter valve 314 can be indicated
to be in a partially deployed configuration, with the inner
catheter 308 somewhat retracted relative to the outer catheter 302.
FIG. 8C, under fluoroscopy, would show two bands 326, 328, with the
second marker band hiding the third marker band 330 (FIG. 8B),
indicating the fully deployed configuration. Other relative
relationships of the marker bands are possible to provided
fluoroscopic indicia with respect to the state of the filter
valve.
[0052] Referring now to FIG. 9, when the filter valve is advanced
to a treatment site within a vessel in the non-deployed
configuration, a very small pressure differential (e.g., 2.5 mmHg)
is generated between the proximal and distal sides of the filter
valve. When the filter valve is partially opened, i.e., deployed
but not extending to the vessel wall (indicated in FIG. 9 as
deployed `25%`), a small but relatively larger pressure
differential (e.g., 5 mmHg) is generated between the proximal and
distal sides of the filter valve. When the filter valve is fully
opened so that the filter valve contacts the vessel wall (indicated
deployed `50%`), a larger pressure differential (e.g., 10 mmHg) is
generated between the proximal and distal sides of the filter
valve. When the filter valve is fully opened and an infusate is
infused through the orifice of the inner catheter to a location
distal of the filter valve, a significantly larger pressure
differential (e.g., 10-20 mmHg) is generated between the proximal
and distal sides of the filter valve. Referring to FIGS. 10A-10C,
the range of generated pressure differentials can be used to
selectively treat vessels of different diameter downstream of the
filter valve. Referring to FIG. 10A, with significant generated
flow and a pressure drop between the proximal and distal sides of
the filter valve, the infusate is directed downstream to at least
the largest target vessel 370. Then, referring to FIG. 10B, by
generating an increase in pressure differential by raising the
fluid pressure of the infusate, additional smaller target branch
vessels 372 resistant to the perfusion at the initial infusate
pressure are perfused. Finally, referring to FIG. 10C, by
increasing the pressure differential again, even smaller target
branch vessels 374 can be perfused. Similarly, to the extent that
treatment is intended to be limited to only certain vessels, the
distal pressure can be limit to below that required to perfuse the
smaller vessels.
[0053] According to one aspect of the invention, the valve is
preferably capable of being configured into its closed position
after the embolization treatment procedure is completed for removal
from the patient. In one configuration for post-treatment removal
from the patient, the valve is simply withdrawn in the deployed
configuration. In another configuration, the inner catheter 308 is
further retracted relative to the outer catheter 302 to invert a
portion or all of the distal filter valve 348 into the proximal
valve 346 to contain embolic agent that may potentially remain on
the filter valve after the treatment. In yet another configuration,
as shown in FIG. 6D, the inner catheter is even further retracted
relative to the outer catheter (in the direction of arrow 386) to
invert the entire filter valve 314 into the outer catheter 302 to
fully contain any embolic agent that may potentially remain on the
filter valve after the treatment.
[0054] Now, as discussed in previously incorporated U.S. Pat. No.
8,696,698, three parameters help define the performance and nature
of the deployed filter valve: the radial (outward) force of the
valve, the time constant over which the valve changes condition
from closed to open, and the pore size of the filter valve.
[0055] In a preferred embodiment, the filter valve expands into the
deployed configuration when, first, the inner and outer catheter
are displaced to move the distal end of the filter valve relative
to the proximal end of the filter valve and thereby shorten and
expand the valve into the deployed configuration. However, once
deployed, the filter valve fully expands to the vessel wall (i.e.,
reaches an open condition) when the pressure at the distal orifice
of the inner catheter is greater than the blood pressure. The
filter valve is also in a deployed but closed condition (with
filter valve retracted from the vessel wall) when blood is flowing
upstream, or in a proximal to distal direction, with pressure
greater than the pressure at the inner catheter orifice. In
addition, when the radial force of expansion on the filter valve
(i.e., the expansion force of the filter valve itself in addition
to the force of pressure in the distal vessel over the distal
surface area of the valve) is greater than the radial force of
compression on the filter valve (i.e., force of pressure in the
proximal vessel over the proximal surface area of the filter
valve), the filter valve fully expands so that the valve assumes
the open configuration. Thus, the radial force of expansion of the
filter valve is chosen to be low (as described in more detail
below) so that normal blood flow in the downstream distal direction
will prevent the deployed filter valve from reaching the open
condition. This low expansion force is different than the expansion
forces of prior art stents, stent grafts, distal protection filters
and other vascular devices, which have significantly higher radial
forces of expansion. It is appreciated that expansion force is
sufficiently low that it will not cause the inner catheter to move
relative to the outer catheter; such relative movement is
preferably effected only by the user of the device.
[0056] The radial force of expansion of a braid is described by
Jedwab and Clerc (Journal of Applied Biomaterials, Vol. 4, 77-85,
1993) and later updated by DeBeule (DeBeule et al., Computer
Methods in Biomechanics and Biomedical Engineering, 2005) as:
F = 2 n [ GI p K 3 ( 2 sin .beta. K 3 - K 1 ) - EI tan .beta. K 3 (
2 cos .beta. K 3 - K 2 ) ] ##EQU00001##
[0057] where K.sub.1, K.sub.2, K.sub.3 are constants given by:
K 1 = sin 2 .beta. 0 D 0 ##EQU00002## K 2 = 2 cos 2 .beta. 0 D 0
##EQU00002.2## K 3 = D 0 cos .beta. 0 ##EQU00002.3##
[0058] and I and I.sub.p are the surface and polar moments of
inertia of the braid filaments, E is the Young's modulus of
elasticity of the filament, and G is the shear modulus of the
filament. These material properties along with the initial braid
angle (.beta..sub.0), final braid angle (.beta.), stent diameter
(D.sub.0), and number of filaments (n) impact the radial force of
the braided valve.
[0059] In one examplar embodiment, the filter valve 314 is composed
of twenty-four polyethylene terephthalate (PET) filaments 350, each
having a diameter of 0.1 mm and pre-formed to an 8 mm diameter
mandrel and a braid angle of 130.degree. (i.e., the filaments are
spring-biased or have a shape memory to assume an angle of
130.degree. relative to each other when the valve assumes a fully
deployed state and opens in a frustoconical configuration). The
filaments 350 preferably have a Young's modulus greater than 200
MPa, and the filter valve 314 preferably has a radial force of less
than 40 mN in the fully deployed position (i.e., where the
filaments assume their shape memory). More preferably, the filter
valve 314 has a radial force in the fully deployed position of less
than 20 mN, and even more preferably the filter valve has a radial
force of approximately 10 mN (where the term "approximately" as
used herein is defined to mean .+-.20%) in the deployed
position.
[0060] In one embodiment, when subject to an infusion pressure at
the distal orifice 358 of the inner catheter, the filter valve 314
moves between deployed positions allowing downstream fluid passage
(closed) and prevening fluid passage (open) in a static fluid
(e.g., glycerin) having a viscosity approximately equal to the
viscosity of blood (i.e., approximately 3.2 cP) in 0.067 second.
For purposes herein, the time it takes to move from the closed
position to the open position in a static fluid is called the "time
constant". According to another aspect of the invention, the filter
valve 314 is arranged such that the time constant of the filter
valve 314 in a fluid having the viscosity of blood is between 0.01
seconds and 1.00 seconds. More preferably, the filter valve 314 is
arranged such that the time constant of the filter valve in a fluid
having the viscosity of blood is between 0.05 and 0.50 seconds. The
time constant of the filter valve 314 may be adjusted by changing
one or more of the parameters described above (e.g., the number of
filaments, the modulus of elasticity of the filaments, the diameter
of the filaments, etc.).
[0061] According to one aspect of the invention, the deployed
filter valve opens and closes sufficiently quickly to achieve high
capture efficiency of embolic agents in the presence of rapidly
changing pressure conditions. More particularly, as shown in FIG.
6C, with the inner and outer catheter displaced to open the filter
valve to the vessel wall 362, when pressure at the distal orifice
358 of the inner catheter 308 (distal of the deployed filter valve
314) increases higher than the pressure in the blood vessel 362,
the seal between the periphery of the filter valve and the vessel
wall is increased, thus blocking refluxing embolics. It is
important to note that pressure is communicated throughout the
vasculature at the speed of sound in blood (1540 m/s) and that the
valve opens and closes in in response to pressure changes within
the blood vessel. Since the expandable filter valve responds to
pressure changes, it reacts far faster than the flow rates of
embolics in the blood (0.1 m/s) thereby preventing reflux of any
embolics.
[0062] As will be appreciated by those skilled in the art, the
braid geometry and material properties of the filaments 350 are
intimately related to the radial force and time constant of the
filter valve. Since, according to one aspect of the invention, the
filter valve is useful in a variety of vessels of different
diameters and flow conditions, each implementation can have a
unique optimization. By way of example only, in one embodiment, the
filter valve 314 has ten filaments 350, whereas in another
embodiment, the filter valve has forty filaments 350. Any suitable
number of filaments can be used. Preferably, the diameter of the
filaments are chosen in the range of 0.025 mm to 0.127 mm, although
other diameters may be utilized. Preferably, the pitch angle (i.e.,
the crossing angle assumed by the braided filaments in the fully
open deployed position) is chosen in the range of 100.degree. to
150.degree., although other pitch angles may be used. Preferably,
the Young's modulus of the filament is at least 100 MPa, and more
preferably at least 200 MPa.
[0063] The filter valve 314 is chosen to have a pore size which is
small enough to capture (filter) embolic agents in the blood stream
as the blood passes through the filter valve. Where large embolic
agents (e.g., 500 .mu.m) are utilized, it may be possible for the
filaments alone to act directly as a filter to prevent embolic
agents from passing through the valve (provided the filaments
present pores of less than, e.g., 500 .mu.m). Alternatively, a
coating 364 is preferably added to the filaments 350, and more
preferably to the formed braid structure, to provide the filter
function. Such a separate polymeric filter is particularly useful
where smaller embolic agents are utilized. The polymeric filter can
be placed onto the braid structure by spraying, spinning,
electrospinning, bonding with an adhesive, thermally fusing,
mechanically capturing the braid, melt bonding, dip coating, or any
other desired method. The polymeric coating 364 can either be a
material with pores such as ePTFE, a solid material that has pores
added such as polyurethane with laser drilled holes, or the filter
coating can be a web of very thin filaments that are laid onto the
braid. Where the coating 364 is a web of thin filaments, the
characteristic pore size of the filter can be determined by
attempting to pass beads of different diameters through the filter
and finding which diameter beads are capable of passing through the
filter in large quantities. The very thin filaments can be spun
onto a rotating mandrel according to U.S. Pat. No. 4,738,740 with
the aid of an electrostatic field or in the absence of an
electrostatic field or both. The filter thus formed can be adhered
to the braid structure with an adhesive or the braid can be placed
on the mandrel and the filter spun over it, or under it, or both
over and under the braid to essentially capture it. The filter 364
can have some pores formed from spraying or electrospinning and
then a secondary step where pores are laser drilled or formed by a
secondary operation. In the preferred embodiment a material capable
of being electrostatically deposited or spun is used to form a
filter on the braid, with the preferred material being capable of
bonding to itself. The filter may be made of polyurethane,
pellethane, polyolefin, polyester, fluoropolymers, acrylic
polymers, acrylates, polycarbonates, or other suitable material.
The polymer is spun onto the braid in a wet state, and therefore it
is desirable that the polymer be soluble in a solvent. In the
preferred embodiment, the filter is formed from polyurethane which
is soluble in dimethylacetamide. The polymer material is spun onto
the braid in a liquid state, with a preferred concentration of
5-10% solids for an electrostatic spin process and 15-25% solids
for a wet spin process.
[0064] According to one aspect of the invention, the filter coating
364 has a characteristic pore size between 10 .mu.m and 500 .mu.m.
More preferably, the filter has a characteristic pore size between
15 .mu.m and 100 .mu.m. Even more preferably, the filter has a
characteristic pore size of less than 40 .mu.m and more preferably
between 20 .mu.m and 40 .mu.m. Most desirably, the filter is
provided with a characteristic pore size that will permit
pressurized blood and contrast agent to pass therethrough while
blocking passage of embolizing agent therethrough. By allowing
regurgitating blood and contrast agent to pass through the filter
in a direction from distal the valve toward the proximal end of the
valve, the contrast agent may be used to indicate when the target
site is fully embolized and can serve to identify a clinical
endpoint of the embolization procedure. Therefore, according to one
aspect of the invention, the valve allows the reflux of the
contrast agent as an indicator of the clinical endpoint while
preventing the reflux of the embolization agents at the same time.
In addition, by allowing blood to flow back through the filter
material, even at a relatively slow rate, backpressure on the
distal side of the valve can be alleviated.
[0065] The filter valve is also preferably provided with a
hydrophilic coating, hydrophobic coating, or other coating that
affects how proteins within blood adhere to the filter and
specifically within the pores of the filter. More specifically, the
coating is resistant to adhesion of blood proteins. One coating
that has been used successfully is ANTI-FOG COATING 7-TS-13
available from Hydromer, Inc. of Branchburg, N.J., which can be
applied to the filter by, e.g., dipping, spraying, roll or flow
coating.
[0066] By appropriate design of the pore size and use of an
appropriate coating, proteins in the blood will almost immediately
fill the pores during use. The proteins on the coated porous filter
operate as a pressure safety valve, such that the pores are filled
with the proteins when subject to an initial fluid pressure greater
than the blood vessel pressure, but the proteins are displaced from
the pores and the pores are opened to blood flow at higher
pressures such as a designated threshold pressure. The designated
threshold pressure is determined to prevent damage to the tissue
and organs, and injury to the patient. Thus, this system allows a
pressure greater than the vessel pressure while limiting very high
pressures which may be unsafe to the patient. As such, the system
provides pressure regulation which is not possible with other
occlusive devices, including balloons. Notwithstanding the
advantage of the above, it is not a requirement of the invention
that the filter be constructed to allow either blood or contrast
agent to pass through in the upstream `reflux` direction under any
determined pressure.
[0067] It is recognized that in the open state, proteins in the
blood may rapidly fill the pores of the filter valve. However, as
discussed above, should a threshold pressure be reached, the filter
valve is designed to permit the blood to reflux through the pores
of the filter valve while still blocking the passage of the embolic
agent. An exemplar threshold pressure is 180 mmHg on the distal
surface of the filter valve, although the device can be designed to
accommodate other threshold pressures. Such can be effected, at
least in part, by the use of an appropriate coating on the filter
that facilitates removal of the blood proteins from within the
filter pores when subject to threshold pressure. This prevents the
vessel in which the device is inserted from being subject to a
pressure that could otherwise result in damage. Nevertheless, it is
not necessary that blood and contrast agent be permitted to reflux
through the valve.
[0068] In an embodiment, the filter coating 350 is preferably
provided as a homogenous coating of filaments, with the proximal
and distal portions 346, 348 of the filter valve 314 having a
uniform coating construct. As the filter valve 314 is provided in
the form of a closed shape, with its proximal end 346 fused to the
outer catheter 302, and its distal end 348 fused to the inner
catheter 308, it is appreciated that any fluid or agent passing
from the vessel and through the filter must through two similar
layers of the filter; i.e., a layer at the proximal side of the
filter valve and a layer at the distal side of the filter
valve.
[0069] In accord with one aspect of the invention, the filter valve
has a different radial force at its proximal portion relative to
its distal portion. This difference in radial force to enable
behavior that is dependent on the direction of the flow (i.e. the
valve behavior). It is preferred that the distal portion have lower
radial force than the proximal portion, as described in FIGS.
11-16, as follows.
[0070] Turning now to FIG. 11, another filter valve 414 at the
distal end of a microvalve device 400 is shown. The filter valve
414 includes a heterogeneous filter coating in which the entire
filter valve is coated. The coating 450 includes smaller pores at
the proximal portion 426 of the filter valve, and larger pores at
the distal portion 428. By way of example only, the smaller pores
can be on the order to one micron, whereas the larger pores can be
on the order to 30 microns. The difference in pore size may be
provided by placing more of the same filamentary coating at the
proximal portion and relatively less at the distal portion to
provide a greater radial force in the proximal portion compared to
the distal portion. The difference in radial force allows the
filter valve to have different performance in forward flow compared
to backflow. In forward flow, the device remains in a conical shape
allowing fluid around it. In backflow, the very weak structure
collapses inward, allowing fluid pressure to seal the device
against the vessel wall and reducing backflow.
[0071] Referring now to FIG. 12, yet another embodiment of a filter
valve 514 at the distal end of a microvalve device 500 is shown.
The filter valve 514 includes a heterogenous filter coating in
which the entire filter valve is coated. The coating 550 includes a
non-porous membrane provided at the proximal portion 526 of the
filter valve, and a porous filamentary coating at the distal
portion 528. The non-porous membrane does not allow flow through
the membrane, thus increasing the antegrade flow around the device
in forward flow. The porous membrane on the distal portion allows
flow through the device, which expands the filter valve to the wall
in backflow to more effectively block embolic agents from flowing
backward.
[0072] Turning now to FIG. 13, another embodiment of a filter valve
614 is shown. The filter valve has a non-porous membrane coating
690 at its inner surface 692 of the proximal portion, and a filter
coating 650 on the outer surface of at least the distal portion of
the filter valve, and preferably the entire filter valve. The
combination of a non-porous membrane and porous membrane on the
proximal portion both increases antegrade flow and radial strength
in forward flow while the porous membrane on the distal portion
reduces radial strength and allows flow into the filter valve in
back flow to seal the vessel and block the reflux of embolic
agents.
[0073] Referring now to FIG. 14, another embodiment of the filter
valve 714 is shown. The filter valve has a construction with a
variable braid angle; i.e., with different braid angles at
different portions of the filter valve. In the illustrated
embodiment, the braid angle is lower at the proximal end and higher
at the distal end. The lower braid angle, e.g., at 792, is
prefrably in the range of 60-90.degree., and the higher braid
angle, e.g., at 794, is preferably greater than 110.degree.. Lower
braid angle has a greater stiffness than lower braid angle, again
providing a different operating behavior in forward flow compared
to backward flow. The variable braid angle aspect of the device can
be used in conjunction with any other embodiment described
herein.
[0074] Turning now to FIG. 15, another embodiment of a filter valve
814 substantially as described with respect to a device 300 above,
is shown. Filter valve 814 is distinguished in having a thicker
braid 827 at its proximal portion 826, and a relatively thinner
braid 829 at its distal portion 828. The so-called thinner braid
829 may be the result of a construction of individually thinner
braid filaments 831 in a similar braid form as in the proximal
portion 826, or a like size braid filament as in the proximal
portion but presented in a denser lattice construction in the
proximal construction and a wider, less dense lattice construction
across the distal portion of the filter valve, or a combination of
these two structural design elements. In addition, the fialments of
the proximal and distal portions may be otherwise designed to exert
differentiated radial force (with greater force at the proximal
portion). By way of the example, the filaments of the braid in the
proximal portion may be selected to have increased resiliency or
spring force, regardless of size or spacing, so as to operate as
desired. The proximal and distal portions 826, 828 are preferably
demarcated by the circumerference about the maximum diameter 833 of
the filter valve. The proximal and distal portions 826, 828 may
have either homogoeneous filter coatings (discussed above with
respect to FIGS. 4 and 5) or hetergeneous filter coatings
(discussed above with respect to FIGS. 11-13), and common
(discussed above with respect to FIGS. 4 and 5) or different braid
angles (discussed above with respect to FIG. 14).
[0075] Referring to FIG. 16, another embodiment of a filter valve
914 for a device as substantialy as described with respect to 300
above, is shown. The filter valve 914 includes a proximal
filamentary braided portion 926, preferably coated with a polymeric
filter material 927, and a distal portion comprising a polymeric
filter material 928. The proximal and distal portions 926, 928 are
preferably demarcated by the circumerference about the maximum
diameter 933 of the filter valve. In accord with this embodiment,
the distal portion 928 is braidless; i.e., does not include any of
the self-expanding filamentary structure. The filter valve 914 may
be formed by positioning the filamentary braid for the proximal
portion 926 on a mandrel (not shown), and spray coating a porous
polymeric membranous material over the proximal braid and also
further distally onto the mandrel--where no braid is provided--for
construction of the braidless distal portion 928. After curing, the
construct is removed from the mandrel. Once the proximal portion
926 of the filter valve 914 is coupled to the outer catheter 904,
and the distal portion 928 of the filter valve 914 is coupled to
the inner catheter 908, the filter valve has preferred properties.
At the distal portion 928, the filter valve 914 is structured
substantially similarly to a fabric. That is, when the inner
catheter 908 is advanced relative to the outer catheter 904 and the
distal portion 928 is placed under tension, the distal portion 928
of the filter valve 914 is strong under tensile force; however,
when the inner catheter 908 is retracted relative to the outer
catheter 904 and the distal portion 928 is placed under
compression, the distal portion of the filter valve is floppy under
compression force.
[0076] Turning now to FIGS. 17A-18, another embodiment of a filter
valve 1014 substantially as described with respect to a device 300
above, is shown. Filter valve 1014 is distinguished in having a
braided structure 1027 of filaments 1027a at its proximal portion
1026, and a spiral arrangement 1029 of filaments 1029a at its
distal portion 1028, seen best in FIG. 18. The braided structure
1027 includes filaments 1027a crossing over and under one another,
e.g., in a woven configuration, to define a crossing angle at the
junctions of the filaments. The spiral arrangement 1029 includes
fewer filaments 1029a than the braided structure 1027, in which
such fewer filaments 1029a extend preferably without crossing over
and under the other filaments in the distal portion 1028, such that
the distal portion is preferably non-braided for desired force
application, as discussed below. The proximal and distal portions
1026, 1028 are preferably demarcated by the circumerference about
the maximum diameter 1033 of the filter valve 1014. Each of the
braided structure 1027 and spiral arrangement 1029 are provided
with a filter coating 1050, preferably as described above with
respect to coating 350 on device 300. The braided and spirally
arranged filaments 1027a, 1029a, including the strand counts in
each of the proximal and distal portions, the lengths of the
respective filaments, and the diameters of the respective
filaments, and the materials of the respective filaments, can be
individually or collectively optimized for an intended resultant
applied radial force within the vessel. By way of example only, the
distal spiral arrangement may include three, six, twelve, or twenty
spiral wound filaments. In addition, the spirally arranged
filaments 1029a in the distal portion 1028 can be evenly
circumferentially spaced about the distal portion; i.e., each
filament 1029a is equidistantly displaced between its two
surrounding filaments (FIG. 18), or can have spirally configured
filaments 1129a arranged in groups 1131 such that the filaments
have a variable relative displacement between each other or between
groups of filaments (FIG. 19). By way of example, FIG. 19 shows
groups 1131 of two filaments, but groups of three, four and six, or
a combination of groups of different numbers of filaments are also
contemplated within the scope of the present disclosure. Also,
while a clockwise (CW) direction of the spiral arrangement is shown
in FIGS. 17A-18, it is appreciated that the filaments may be
configured in a counterclockwise (CCW) configuration, or for some
of the filaments 1129a to extend in the CW direction and the
remainder of the filaments 1129b to extends in the CCW direction,
as shown in FIG. 19. However, where some filaments extend in each
of the CW and CCW direction, such filaments preferably extend
between the counter-rotational groups or sets (as shown) so as to
prevent interference, or in separate `planes` or layers of the
distal portion such that the filaments do not cross over and under
the counter-directional filaments.
[0077] The filter valve 1014 may be formed by providing a braided
filamentary tubular construct, and selective selective removal
certain filamnts and spiral wound manipulation of remaining
filaments at a distal portion of a braided filamentary tubular
construct, while keeping the filaments structure of the proximal
braided portion intact. Then, the resultant filamentary construct
is filter coated. In such construct, it is appreciated that
filaments defining the braided structure of the proximal portion
and filaments defining the spiral wound structure of the distal
portion may be continuous. As such, in this construct, the proximal
filaments referred to herein are to be considered the proximal
portion of such filaments, whereas the distal filaments referred to
herein are to be considere the distal portion of such same
filaments. Alternatively, the filamentary constructs of the
proximal and distal portions 1026, 1028 may be separately formed
and subsequently joined, and then coated with the filter coating
1050. Other manufacturing processes may also be used.
[0078] In use, with the filter valve 1014 provided on the distal
ends of outer and inner catheters 1004, 1008, as described above,
the inner catheter 1008 is distally displaced relative to the outer
catheter 1004 to reduce the diameter of the filter valve 104, as
shown in FIG. 17A for insertion into a patient. This configuration
facilitates tracking over a guidewire to a location of therapeutic
treatment. The spiral filament configuration of the distal portion
1028 of the filter valve offers a lower profile at the distal end
of the device. Once at the therapy site, the guidewire can be
removed. Then, the user begins to proximally displace the inner
catheter 1008 relative to the outer catheter 1004 to retract the
distal end portion 1028 relative to the proximal braided portion
1026 in preparation for treatment (FIG. 17B). Upon full retraction
of the distal portion 1028, the spiral filament "struts" 1029a push
radially outward, driving the braided section 1028 diametrically
radially outward until the circumference reaches its largest
potential diameter 1033 (FIG. 17C); i.e., in contact with the
vessel wall. At this point the spiral filament "struts" start to
reverse in rotational direction, and essentially pull within the
braided proximal portion of the filter valve. As such, in this
embodiment, a hinge-point is created at the transition from spiral
to braid. Further, the filter valve 1014 has a higher potential
force at the braided proximal portion 1026 than at spiral filament
distal portion 1028.
[0079] In each of the embodiments of FIGS. 11-19, the distal
portion of the filter valve exerts a signficantly reduced radial
force relative to the proximal portion of the filter valve, which
results in optimizing the function of the filter valve as a valve.
In forward (downstream) flow of the fluid within the vessel, as the
fluid contacts the proximal side of the expanded proximal portion,
the fluid flows around filter valve. In distinction, in backward or
reflux (upstream) flow of fluid within the vessel as the fluid
contact the distal side of the expanded distasl portion, the fluid
flows into--and not around--the filter valve. In such upstream
flow, certain fluids, namely blood, are able to flow through the
double layer filter material of the filter valve, while the pores
of the filter material are of a sufficeintly small size to capture
embolic agents and other therapeutic agents of interest.
[0080] In any of the embodiments, the physician will track and
advance the inner catheter of the microvalve device over a
guidewire out to a target location, and then remove the guidewire.
An embolic agent is then infused through the inner catheter to
deliver the agent distal of the microvalve, and the device is
utilized as intended and in accord with its specific structural
design. Then, after infusion, when it is necessary to remove the
device from the patient, the physician has two options to prepare
or configure the microvalve device for removal. The inner catheter
can be pushed or otherwise displaced forward relative to the distal
end of the outer catheter to result in collapse of the microvalve
to reduce its diameter to facilitate its removal from the vessels
of the body. Alternatively, after infusion of the agent, the inner
catheter can be proximally withdrawn and inverted into the distal
end of the outer catheter to retain at least a portion, and
preferably all, of the microvalve device within the outer catheter
and capture any embolic agent on such portion of the microvalve
within the outer catheter during subsequent withdrawal of the
device from the patient. The second option is preferred for
radioactive embolic agents where the potential for spreading
radioactive embolics during removal can otherwise exist.
[0081] In any of the embodiments described herein, the components
of the valve may be coated to reduce friction in deployment and
retraction. The components may also be coated to reduce thrombus
formation along the valve or to be compatible with therapeutics,
biologics, or embolics. The components may be coated to increase
binding of embolization agents so that they are removed from the
vessel during retraction.
[0082] According to one aspect of the invention, the catheter body
and mesh may be separately labeled for easy visualization under
fluoroscopy. The catheter body can be labeled by use of any means
known in the art; for example, compounding a radio-opaque material
into the catheter tubing. The radio-opaque material can be barium
sulfate, bismuth subcarbonate or other material. Alternatively or
additionally, radio-opaque medium can be compounded into the
materials of the braid and the filter. Or, as previously described,
one or more of the filaments may be chosen to be made of a
radio-opaque material such as platinum iridium.
[0083] In each of the embodiments, the inner catheter may be a
single lumen or a multi-lumen catheter. Preferably, the catheter
has at least one lumen used to deliver the embolization agents, and
one or more additional lumen may be provided, if desired, for
passage of a guidewire or other devices or to administer fluids,
e.g., for flushing the artery after the administration of
embolization agents.
[0084] The above apparatus and methods have been primarily directed
to a system which permits proximal and distal flow of biological
fluid (e.g., blood) within a body vessel, and which prevents reflux
of an infusate past the valve in a proximal direction. It is
appreciated that the valve may also be optimized to reduce blood
flow in the distal direction. In any of the embodiments, the radial
force of the filter valve can be tuned by adjusting the braid
angle. Tuning the radial force allows the blood flow to be reduced
by up to more than 50 percent. By way of example, providing a braid
angle greater than 130.degree. will significantly reduce blood flow
past the valve in the distal direction, with a braid angle of
approximately 150.degree. slowing the blood flow by 50 to 60
percent. Other braid angles can provide different reductions in
distal blood flow. The reduced distal blood flow can be used in
place of a `wedge` technique, in which distal blood flow is reduced
for treatment of brain and spinal arteriovenous malformations. Once
the blood flow is slowed by the valve, a glue such as a
cyanoacrylic can be applied at the target site.
[0085] While the above description has been primarily directed to
use of the device for infusing a therapeutic agent, it is
appreciated that the device has significant functionality even when
delivery of a therapeutic agent is not the primary function. By way
of example, the device can be used to retrieve a thrombus and
prevent dislodged embolic particles from escaping into the
patient's blood. Briefly, a thrombus retrieval device can be passed
through the inner catheter 308 to release and retrieve a thrombus.
The filter valve 314 operates to prevent the thrombus and spray of
embolic particles from passing beyond the filter valve and into the
vessel. Then when the thrombus is captured, the thrombus along with
any embolic particles can be contained within the filter valve as
the filter valve is inverted into the outer catheter for removal
from the patient, in a similar method to that discussed above. For
such use, the inner catheter may include a single lumen or multiple
lumens; i.e., one for the thrombus retrieval device and one or more
for additional devices or therapeutic agent infusion.
[0086] There have been described and illustrated herein multiple
embodiments of devices and methods for reducing or preventing
reflux of embolization agents in a vessel. While particular
embodiments of the invention have been described, it is not
intended that the invention be limited thereto, as it is intended
that the invention be as broad in scope as the art will allow and
that the specification be read likewise. Thus, while various
materials have been listed for the valve filaments, the valve
filter, and the inner and outer catheters, it will be appreciated
that other materials can be utilized for each of them in each of
the various embodiments in combination and without limitation.
Also, while the invention has been described with respect to
particular arteries of humans, it will be appreciated that the
invention can have application to any blood vessel and other
vessels, including ducts, of humans and animals. In particular, the
apparatus can also be used in treatments of tumors, such as liver,
renal or pancreatic carcinomas. Further, the embodiments have been
described with respect to their distal ends because their proximal
ends can take any of various forms, including forms well known in
the art. By way of example only, the proximal end can include two
handles with one handle connected to the inner catheter, and
another handle connected to the outer catheter. Movement of one
handle in a first direction relative to the other handle can be
used to extend the filter valve in the non-deployed configuration
for advancement to the treatment site, and movement of that handle
in an opposite second direction can be used to deploy the filter
valve. Depending upon the handle arrangement, filter valve
deployment can occur when the handles are moved away from each
other or towards each other. As is well known, the handles can be
arranged to provide for linear movement relative to each other or
rotational movement. If desired, the proximal end of the inner
catheter can be provided with hash-marks or other indications at
intervals along the catheter so that movement of the handles
relative to each other can be visually calibrated and give an
indication of the extent to which the valve is opened. It will
therefore be appreciated by those skilled in the art that yet other
modifications could be made to the provided invention without
deviating from its spirit and scope as claimed.
* * * * *