U.S. patent application number 15/442588 was filed with the patent office on 2017-12-14 for delivery system for inflatable implant.
The applicant listed for this patent is ATTENUEX TECHNOLOGIES, INC.. Invention is credited to Hung Cao, Kevin G. Connors.
Application Number | 20170354491 15/442588 |
Document ID | / |
Family ID | 37900375 |
Filed Date | 2017-12-14 |
United States Patent
Application |
20170354491 |
Kind Code |
A1 |
Connors; Kevin G. ; et
al. |
December 14, 2017 |
DELIVERY SYSTEM FOR INFLATABLE IMPLANT
Abstract
An implant delivery system can be used to deliver an implant
into a body. The implant delivery system can include an inflation
tube and a tubular member surrounding the inflation tube. The
inflation tube can be used to provide an inflation medium to the
implant. The tubular member can have a distal tip and an opening
spaced from the tip to allow the implant to be released through the
opening into an anatomical structure within the body.
Inventors: |
Connors; Kevin G.;
(Wellesley, MA) ; Cao; Hung; (Corona, CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
ATTENUEX TECHNOLOGIES, INC. |
Newton |
MA |
US |
|
|
Family ID: |
37900375 |
Appl. No.: |
15/442588 |
Filed: |
February 24, 2017 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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14628108 |
Feb 20, 2015 |
9615911 |
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15442588 |
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13227781 |
Sep 8, 2011 |
8961392 |
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14628108 |
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12475918 |
Jun 1, 2009 |
8016740 |
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13227781 |
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11527333 |
Sep 26, 2006 |
7540876 |
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12475918 |
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11314601 |
Dec 20, 2005 |
7374532 |
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11527333 |
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10618571 |
Jul 11, 2003 |
6976951 |
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11314601 |
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10391446 |
Mar 17, 2003 |
6976950 |
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10618571 |
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09723309 |
Nov 27, 2000 |
6682473 |
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10391446 |
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60721834 |
Sep 26, 2005 |
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60415949 |
Oct 3, 2002 |
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60197095 |
Apr 14, 2000 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61B 2017/00243
20130101; A61F 2002/068 20130101; A61F 2/95 20130101; A61F 2/89
20130101; A61F 2/0063 20130101; A61F 2220/005 20130101; A61F 2/07
20130101; A61F 2220/0058 20130101; A61F 2/90 20130101; A61F 2/06
20130101; A61F 2250/0013 20130101 |
International
Class: |
A61F 2/06 20130101
A61F002/06; A61F 2/07 20130101 A61F002/07; A61F 2/95 20130101
A61F002/95 |
Claims
1.-7. (canceled)
8. An attenuator for attenuating pressure changes in a
cardiovascular system, the attenuator comprising: at least one
connection zone for connecting the attenuator to an implantation
location in pressure communication with the cardiovascular system;
a compliant attenuation zone configured to move from a first volume
having a first internal pressure to a second volume having a second
internal pressure in response to a change in a pressure of an
environment surrounding the attenuator, wherein movement of the
compliant attenuation zone from the first volume to the second
volume attenuates the change in the pressure of the environment
surrounding the attenuator.
9. The attenuator for attenuating pressure changes in a
cardiovascular system of claim 8, wherein the attenuator is
configured to be connected to a wall of a heart in the
cardiovascular system.
10. The attenuator for attenuating pressure changes in a
cardiovascular system of claim 8, wherein the attenuator is
configured to be connected to a blood vessel in the cardiovascular
system.
11. An implantable pressure attenuator, comprising: at least one
connection zone for connection to an implantation location; at
least one attenuation zone having a first state and a second state;
and wherein the implantable pressure attenuator is configured to
attenuate a change in a physiological pressure at the implantation
location though a change of the at least one attenuation zone from
the first state to the second state.
12. The implantable pressure attenuator of claim 11, wherein the
implantable pressure attenuator is configured to attenuate a change
in a blood pressure.
13. The implantable pressure attenuator of claim 11, wherein the
change of the at least one attenuation zone from the first state to
the second state comprises a change in volume of the at least one
attenuation zone.
14. The implantable pressure attenuator of claim 11, wherein the
change in volume of the at least one attenuation zone comprises a
reduction in volume of the at least one attenuation zone.
15. The implantable pressure attenuator of claim 11, wherein the
implantable pressure attenuator is configured to be implanted in
pressure communication with a blood vessel.
16. The implantable pressure attenuator of claim 15, wherein the
implantable pressure attenuator is in fluid communication with the
blood vessel.
17. The implantable pressure attenuator of claim 15, wherein the
implantable pressure attenuator is not in fluid communication with
the blood vessel.
18. The implantable pressure attenuator of claim 15, wherein the
blood vessel comprises at least one of a vessel between an iliac
artery and a heart, a carotid artery, a vessel carrying blood to a
brain, a vessel carrying blood from the brain, and an aorta.
19. The implantable pressure attenuator of claim 11, wherein the
implantable pressure attenuator is configured to reduce at least
one of mean arterial pressure, systolic pressure, diastolic
pressure, and pulse pressure.
20. The implantable pressure attenuator of claim 11, wherein a
volume of the attenuation zone when in the first state is greater
than a volume of the attenuation zone when in the second state, and
wherein an internal pressure of the attenuation zone when in the
second state is greater than an internal pressure of the
attenuation zone when in the first state.
21. The implantable pressure attenuator of claim 11, wherein the
implantable pressure attenuator comprises a sleeve configured to
extend at least partially around a blood vessel, wherein an inner
surface of the sleeve is configured to contact at least a portion
of an external surface of the blood vessel.
22. The implantable pressure attenuator of claim 11, wherein the
implantable pressure attenuator comprises a substantially tubular
attenuation zone between a first connection zone of the at least
one connection zone and a second connection zone of the at least
one connection zone.
23. The implantable pressure attenuator of claim 22, wherein the
implantable pressure attenuator is configured to be implanted
within a blood vessel without disrupting a wall of the blood vessel
at the implantation location, wherein the first connection zone of
the at least one connection zone and the second connection zone of
the at least one connection zone are configured to minimize
movement of the attenuation zone with respect to an inner surface
of the blood vessel.
24. The implantable pressure attenuator of claim 22, wherein the
implantable pressure attenuator is configured to be implanted
between a first portion of a severed blood vessel and a second
portion of the severed blood vessel, wherein the first connection
zone of the at least one connection zone is configured to be
connected to the first portion of the severed blood vessel and the
second connection zone of the at least one connection zone is
configured to be connected to the second portion of the severed
blood vessel, and wherein the substantially tubular attenuation
zone extends between the first portion of the severed blood vessel
and the second portion of the severed blood vessel such that blood
may flow from the first portion of the severed blood vessel to the
second portion of the severed blood vessel through the
substantially tubular attenuation zone.
25. The implantable pressure attenuator of claim 11, wherein each
connection zone of the at least one connection zone is configured
to be sutured to a blood vessel at the implantation location.
26. The implantable pressure attenuator of claim 11, wherein each
connection zone of the at least one connection zone comprises an
expandable structure configured to engage at least a portion of the
implantation location.
27. The implantable pressure attenuator of claim 26, wherein each
expandable structure of each connection zone of the at least one
connection zone comprises at least one of a balloon-expandable
stent and a self-expandable stent.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation of U.S. patent
application Ser. No. 14/628,108 (Dkt. No. SOLACE.012C3), filed on
Feb. 20, 2015, which is a continuation of U.S. patent application
Ser. No. 13/227,781 (Dkt. No. SOLACE.012C2), filed on Sep. 8, 2011,
now U.S. Pat. No. 8,961,392, which is a continuation of U.S. patent
application Ser. No. 12/475,918 (Dkt. No. SOLACE.012C1), filed on
Jun. 1, 2009, now U.S. Pat. No. 8,016,740, which is a continuation
of U.S. patent application Ser. No. 11/527,333 (Dkt. No.
SOLACE.012A), filed on Sep. 26, 2006, now U.S. Pat. No. 7,540,876,
which claims priority to U.S. Provisional Patent Appl. No.
60/721,834, filed on Sep. 26, 2005. U.S. patent application Ser.
No. 11/527,333 is also a continuation-in-part of U.S. patent
application Ser. No. 11/314,601 (Dkt. No. SOLACE.4CP1C4C), filed on
Dec. 20, 2005, now U.S. Pat. No. 7,374,532, which is a continuation
of U.S. patent application Ser. No. 10/618,571 (Dkt. No.
SOLACE.4CP1C4), filed on Jul. 11, 2003, now U.S. Pat. No.
6,976,951, which is a continuation of U.S. patent application Ser.
No. 10/391,446 (Dkt. No. SOLACE.004CP1), filed on Mar. 17, 2003,
now U.S. Pat. No. 6,976,950, which claims priority to U.S.
Provisional Patent Appl. No. 60/415,949, filed on Oct. 3, 2002.
U.S. patent application Ser. No. 10/391,446 is also a
continuation-in-part of U.S. patent application Ser. No. 09/723,309
(Dkt. No. SOLACE.004A), filed on Nov. 27, 2000, now U.S. Pat. No.
6,682,473, which claims priority to U.S. Provisional Patent Appl.
No. 60/197,095 (Dkt. No. SOLACE.004PR), filed on Apr. 14, 2000. The
disclosures of the aforementioned applications are hereby
incorporated by reference in their entirety. Any and all priority
claims identified in the Application Data Sheet, or any correction
thereto, are hereby incorporated by reference under 37 CFR
1.57.
BACKGROUND
Field of the Invention
[0002] The application relates generally to methods and apparatus
for attenuating and/or baffling transient pressure waves in
relatively incompressible materials in organs and systems of the
human body, including, but not limited to the following systems:
cardiovascular, pulmonary, renal/urological, gastrointestinal,
hepatic/biliary, gynecological, central nervous, musculoskeletal,
otorhinolaryngological and ophthalmic.
[0003] The present application also relates generally to the fields
of end-stage heart failure and noncompliant vasculature, and in
particular to the treatment of disorders caused by fluctuations of
intravascular pressure. In one aspect, methods and devices are
provided for the treatment of hypertension and its adverse
sequelae.
Description of the Related Art
[0004] Pressure waves are known to propagate through incompressible
fluids in various organs of the body. Such pressure waves can be
cyclical and part of normal body function, such as in the
cardiovascular system, or more random, such as arise in response to
environmental stimuli.
[0005] In the cardiovascular system, the beating of the heart
cyclically pumps blood through the vasculature. This process
normally generates pressure waves in the vascular system.
Hypertension (high blood pressure), a malady from which many adults
suffer, is associated with cardiovascular disease and stroke.
Though there are many causes of hypertension, primary (or
essential) hypertension is responsible for about 95% of the cases.
High systolic blood pressure, i.e., the pressure in the vasculature
associated with the expelling of blood from the heart into the
aorta, has become the predominant concern in hypertensive patients.
The determinants of systolic blood pressure are blood flow,
arterial compliance, and arterial wave propagation. Aging results
in arterial stiffening which decreases arterial compliance and
increases systolic hypertension. As discussed further below
reducing hypertension is desirable.
[0006] Pressure waves also may be caused by a number of events,
e.g., events within the body, such as breathing in the lungs,
peristalsis actions in the GI tract, movement of the muscles of the
body, or events such as coughing, laughing, external trauma to the
body, and movement of the body relative to gravity. As the
elasticity of the surrounding tissues and organs, sometimes
referred to as compliance, decreases, the propagation of these
undesirable pressure waves increases. These undesirable pressure
waves have many undesirable effects ranging from discomfort, to
stress on the organs and tissue, to fluid leakage such as urinary
incontinence, to renal failure, stroke, heart attack and
blindness.
[0007] Pressure accumulators and wave diffusers are types of
devices that can modulate pressure waves in various nonanalogous
settings. Accumulator technology is well known and used in
hydraulic systems in aircraft, manufacturing equipment, and water
supply and distribution since the 1940s. Common types of
accumulators include bladder accumulators, piston accumulators,
non-separator (air over fluid), and weight loaded type
accumulators.
[0008] Wave diffusers also affect the transmission of pressure
waves in incompressible systems in various settings. The function
of such diffusers is to interrupt the progress of a pressure wave
and distribute the energy of the wave in so many directions so as
to destroy the integrity of a uniform wavefront and its resultant
effects. Wave diffusers may be used to protect a specified area
from the impact of a wavefront.
[0009] Currently, the most common approach to treating hypertension
is drug therapy. These drugs include oral medications (systemic)
and drugs delivered directly into the bloodstream. These drugs may
suffer from side effects, lack of effectiveness and high morbidity.
Oral medications typically do not allow immediate relief of
symptoms and include side effects such as dry mouth and
constipation. Drugs delivered directly into the bloodstream often
require continuous or intermittent catheterization for introduction
of the therapeutic agents at the clinically appropriate time.
[0010] In light of the foregoing, a number of attempts have been
made to combat these disorders. These attempts have included
pharmaceuticals, meditation and relaxation, and neurostimulation.
However, these prior art approaches do not address the reduction in
dynamic compliance, e.g., in the vasculature, which results in
increased blood pressure and the associated cardiovascular
disorders.
SUMMARY
[0011] There is provided in accordance with various aspects of the
present invention devices and methods of treating a patient.
[0012] There is provided in one aspect a device for treating
hypertension and other cardiovascular maladies. The device
comprises a pressure attenuator that can mitigate or attenuate peak
pressures. Such a device acting as a pressure attenuator may be
used to decrease systolic blood pressure. This may decrease or
eliminate the need for antihypertensive medications.
[0013] There is provided in accordance with another aspect of the
present invention, a device for treating altered vascular
compliance and, comprising an attenuation device having an expanded
volume within the range of from about 1 cc to about 400 cc. It may
also include a valve for permitting filling of the attenuation
device through a delivery system.
[0014] In another aspect, an implantable blood pressure regulator
is provided. The blood pressure regulator includes at least one
connection zone and an attenuation zone. The connection zone is
suitable for connection to a body conduit, such as a blood vessel.
The attenuation zone is movable from a first state to a second
state in response to a physiological pressure spike. The movement
from the first state to the second state lowers a level of pressure
in the body conduit.
[0015] In another aspect, a method is provided for treating a
patient. The method includes providing a variable volume structure
and placing the variable volume structure in pressure communication
with the patients' vasculature. The volume of the structure is
reduced from a first volume to a second volume in response to a
pressure spike in the vessel to reduce the magnitude of the
pressure spike.
[0016] In another aspect, a method is provided for treating a
patient. The method includes providing a conduit having first and
second ends and an attenuation zone disposed therebetween. The
attenuation zone is configured to expand from a first volume to a
second volume in response to a pressure spike in the vessel. At
least one of the first and second ends of the conduit is coupled
with the patient's vasculature.
[0017] According to some embodiments, an implant delivery system
can be used to deliver an implant into a body. The implant delivery
system can include an inflation tube and a tubular member
surrounding the inflation tube. The inflation tube can be used to
provide an inflation medium to the implant. In some embodiments
inflation tube the may be coupled to the inflatable implant. The
tubular member can have a distal tip and an opening spaced from the
tip to allow the implant to be released through the opening into an
anatomical structure within the body. The distal tip may be an
atraumatic tip.
[0018] In some embodiments, the implant delivery system can have a
first configuration in which the opening is blocked and a second
configuration in which the opening is open to allow the implant to
be released into the anatomical structure. Further, the implant
delivery system may include a sheath. The sheath can surround the
tubular member and in some embodiments may cover the opening when
the implant delivery system is in the first configuration.
[0019] Further features and advantages of the present invention
will become apparent to those of skill in the art in view of the
detailed description of preferred embodiments which follows, when
considered together with the attached drawings and claims.
BRIEF DESCRIPTION OF THE DRAWINGS
[0020] FIG. 1A illustrates an estimate of the number of adult
Americans that suffer from hypertension.
[0021] FIG. 1B illustrates an estimate of the increase in frequency
of hypertension with age.
[0022] FIG. 1C illustrates some of the cardiovascular maladies
associated with hypertension.
[0023] FIG. 1D illustrates pressure in a patient's vasculature in
response to a heart cycle.
[0024] FIG. 1E illustrates blood pressure, left ventricle
volumetric output, and ECG output over a heart cycle.
[0025] FIG. 1F illustrates a compliance curve for biological tissue
such as an artery.
[0026] FIG. 1G illustrates a relationship between changes in volume
and pressure in aortas having high and low compliance.
[0027] FIG. 2A illustrates intravesical pressure exceeding maximum
urethral pressure during normal voiding.
[0028] FIG. 2B illustrates the intravesical pressure exceeding the
maximum urethral pressure in a noncompliant bladder.
[0029] FIG. 3 illustrates an intravesical pressure spike exceeding
the maximum urethral pressure during stress incontinence.
[0030] FIG. 4A illustrates the relationship between intravesical
pressure and detrusor pressure during cough-induced urgency or
frequency.
[0031] FIG. 4B illustrates the relationship between intravesical
pressure and detrusor pressure during non-cough-induced urgency or
frequency.
[0032] FIG. 5 is a schematic top plan view of an inflatable
attenuation device in accordance with one aspect of the
invention.
[0033] FIG. 5A is a side elevational cross-section through the
attenuation device of FIG. 5.
[0034] FIG. 6 is a side elevational schematic view of a delivery
system for deploying an attenuation device in accordance with one
aspect of the present invention.
[0035] FIG. 6A is a side elevational schematic view of one
embodiment of the present invention.
[0036] FIG. 6B is a cross-section through the line 6B-6B in FIG.
6.
[0037] FIG. 7A is a fragmentary schematic view of the filling tube
of a delivery system engaged within the valve of an attenuation
device.
[0038] FIG. 7B is a fragmentary schematic view as in FIG. 7A, with
the filling tube proximally retracted from the valve.
[0039] FIG. 7C illustrates details of a valve construction for an
attenuation device.
[0040] FIGS. 8A-8E schematically illustrate different valve
constructions for an inflatable attenuation device in accordance
with the present invention.
[0041] FIG. 9 is a schematic representation of the delivery system
of FIG. 6, transurethrally positioned within the bladder.
[0042] FIG. 10 is a schematic illustration as in FIG. 9, with the
attenuation device inflated.
[0043] FIG. 11 is a schematic view of one embodiment of a delivery
system in accordance with the present invention, transurethrally
positioned within the bladder.
[0044] FIG. 11A is a cross-section through one embodiment of the
delivery system of FIG. 11.
[0045] FIG. 12 is a side elevational schematic view of an
attenuation device removal system in accordance with one aspect of
the present invention.
[0046] FIG. 13 is a schematic view of a toroidal shaped attenuation
device accordance with one embodiment of the present invention.
[0047] FIG. 13A is a side elevational cross-section view through
one embodiment of the attenuation device of FIG. 13.
[0048] FIG. 14 is a schematic view of a toroidal shaped attenuation
device as in FIG. 13, with an integral baffle therein.
[0049] FIG. 14A is a side elevational cross-section view through
one embodiment of the attenuation device of FIG. 14.
[0050] FIG. 15 is a schematic illustration of the attenuation
device disrupting the unitary progression of a pressure
wavefront.
[0051] FIGS. 16A-D are schematic representations of a variety of
inflatable attenuation devices in accordance with the present
invention.
[0052] FIG. 17A is a side elevational schematic view of a
bellow-type mechanically assisted attenuation device in an expanded
configuration.
[0053] FIG. 17B is a side elevational schematic view of the
attenuation device of FIG. 17A, in a compressed configuration
attenuating a pressure spike.
[0054] FIG. 17C is a side elevational schematic view of a
bellow-type mechanically assisted attenuation device in an expanded
configuration deployed in a blood vessel.
[0055] FIG. 17D is a side elevational schematic view of the
attenuation device of FIG. 17C, in a compressed configuration
attenuating a pressure spike in a blood vessel.
[0056] FIG. 17E is a side view of the attenuation device from FIG.
17A in a container, in proximity to a blood vessel with the bellow
expanded.
[0057] FIG. 17F is a side view of the attenuation device of FIG.
17E with the bellows in a compressed configuration attenuating a
pressure spike.
[0058] FIG. 18 is a side elevational schematic view of a
self-expanding graft type mechanically assisted attenuation
device.
[0059] FIG. 19A is a side elevational schematic view of a multiple
chamber attenuation device in accordance with a further aspect of
the present invention.
[0060] FIG. 19B is a schematic illustration of the multiple chamber
attenuation device of FIG. 19A, in a deployed orientation to ensure
retention within the bladder.
[0061] FIG. 20 is a side elevational schematic view of an
inflatable balloon-type attenuation device, having a locatable
balloon valve thereon.
[0062] FIG. 21 is a schematic perspective view of the attenuation
device of FIG. 20, aligned with the distal end of a delivery or
removal system.
[0063] FIG. 22 is a fragmentary cross-sectional view through the
distal end of a delivery or removal system, and the proximal end of
the valve on an attenuation device, illustrating the valve in a
filling or draining orientation.
[0064] FIG. 23 is a fragmentary cross-section as in FIG. 22,
showing the valve in a sealed orientation.
[0065] FIG. 24 is a schematic cross-section through a bladder,
showing an attenuation device therein, having an attached, external
tether.
[0066] FIG. 25 is a schematic cross-section through a bladder,
showing a two-component attenuation device in which a primary
compressible component is positioned within the bladder and a
secondary inflatable component is positioned within the
urethra.
[0067] FIG. 25A is a cross-sectional schematic view as in FIG. 25,
illustrating the compression of the primary attenuation device in
response to elevated abdominal pressure, and the corresponding
expansion of the secondary inflatable component.
[0068] FIG. 25B is an enlarged fragmentary schematic view of the
inflatable component in FIG. 25A.
[0069] FIG. 25C is a pressure curve showing the intravesical
pressure compared to the secondary balloon pressure.
[0070] FIG. 26 illustrates the effect on intravesical pressure of
the presence of an implanted attenuation device in accordance with
the present invention.
[0071] FIG. 27 is a schematic cross-sectional view through a
bladder, showing an attenuation device anchored to the bladder
wall.
[0072] FIG. 28 is a schematic cross-sectional view showing a
bladder, and the transurethral placement of a dynamic compliancy
measurement catheter in accordance with the present invention.
[0073] FIG. 29 is a schematic cross-sectional view through a blood
vessel, illustrating an attenuation device deployed therein.
[0074] FIG. 29A is a schematic cross-sectional view through a blood
vessel, illustrating an attenuation device deployed therein, the
attenuation device being in a compressed configuration attenuating
a pressure spike in the blood vessel.
[0075] FIG. 29B is a schematic cross-sectional view through a blood
vessel, illustrating an attenuation device therein returning to an
expanded configuration after attenuating a pressure spike in the
blood vessel.
[0076] FIG. 29C is a schematic cross-sectional view through a
vessel, illustrating an attenuation device in proximity to the
vessel, in a compressed configuration attenuating a pressure
spike.
[0077] FIG. 29D is a schematic cross-sectional view through a
vessel, illustrating an attenuation device in proximity to a blood
vessel, the device returning to an expanded state after attenuating
a pressure spike.
[0078] FIG. 29E is a schematic cross-sectional view of an
attenuation device collapsed, in a compressed configuration, which
can correspond to a relatively low pressure condition.
[0079] FIG. 29F is a schematic cross-sectional view of an
attenuation device expanded to a configuration suitable for
attenuating a pressure spike.
[0080] FIG. 29G is a schematic cross-sectional view of an
attenuation device as it collapses to a compressed configuration
after attenuating a pressure spike.
[0081] FIG. 29H is a schematic cross-sectional view of an
attenuation device mounted to an expandable/collapsible attachment
structure.
[0082] FIG. 29I is a schematic cross-sectional view of an
attenuation device mounted to an expandable/collapsible attachment
structure, the device being in an expanded configuration.
[0083] FIG. 29J is a schematic cross-sectional view of a,
attenuation device mounted to an expandable/collapsible attachment
structure, as it returns to a compressed configuration.
[0084] FIG. 29K is a schematic cross-sectional view through a
vessel, illustrating an attenuation device anastomosed in series in
the vessel.
[0085] FIG. 29L is a schematic cross-sectional view through a
vessel, illustrating an attenuation device mounted to an expandable
support deployed within a vessel.
[0086] FIG. 29M is a schematic cross-sectional view through a
vessel, illustrating a pressure regulator replacing a removed
portion of a blood vessel.
[0087] FIG. 29N is a schematic cross-sectional view through a
vessel, illustrating a pressure regulator deployed within an
abdominal aortic aneurysm.
[0088] FIG. 30A is a schematic cross-section of a left atrial
appendage of the heart, having an attenuation device positioned
therein.
[0089] FIG. 30B is a schematic cross-section as in 30A, showing a
bellows-type attenuation device positioned in the left atrial
appendage.
[0090] FIG. 31 is a schematic cross-section of a tubular
attenuation device positioned within the colon.
[0091] FIG. 32A is a schematic top plan view of an inflatable
attenuation device with a duckbill valve design.
[0092] FIG. 32B is a close-up view of the duckbill valve in FIG.
32A.
[0093] FIG. 33A is a schematic top plan view of an inflatable
attenuation device with a ring valve design.
[0094] FIG. 33B is a schematic top plan view of an inflatable
attenuation device with a fill/plug design.
[0095] FIG. 33C is a schematic top plan view of an inflatable
attenuation device with a dome valve design.
[0096] FIG. 34A is an elevated side view of one embodiment of a
delivery system for the attenuation device in accordance with one
aspect of the present invention.
[0097] FIG. 34B is an elevated side view of one embodiment of a
delivery system for the attenuation device with the attenuation
device exposed and ejected.
[0098] FIG. 35A is an elevated side view of one embodiment of a
delivery system for the attenuation device in accordance with one
aspect of the present invention.
[0099] FIG. 35B is an elevated side view of the inflatable
attenuation device in FIG. 35A with the sheath slid proximally and
the attenuation device exposed.
[0100] FIG. 36 is a schematic top plan view of an inflatable
attenuation device with a valve that prevents the influx and/or
efflux of media to/from the attenuation device.
[0101] FIG. 37 is a cross-section through the line 288-288 in FIG.
36.
[0102] FIG. 38 is a schematic top plan view of a valve with two
duckbill structures that prevent the flow of media in both
directions.
[0103] FIGS. 39A-D presents graphs of attenuation/pressure
reduction vs. time for various attenuation device air volumes.
[0104] FIGS. 40A and 40B illustrate the connective and elastic
tissues in the submucosal layer of the bladder.
[0105] FIG. 41 shows a typical cystometrogram.
[0106] FIGS. 42 and 43 provide side elevational cross-sectional
views of a partially collapsed bladder.
[0107] FIGS. 44A-D shows pressure vs. time curves generated by a
bench top bladder simulator.
[0108] FIG. 45 is a schematic view of one embodiment of an
accumulator.
[0109] FIG. 46 is a schematic view of a simple accumulator.
[0110] FIG. 47A is a schematic cross-sectional view through one
embodiment of an implantable self-inflating attenuation device.
[0111] FIG. 47B is a schematic cross-sectional view through one
embodiment of an implantable self-inflating attenuation device.
[0112] FIG. 47C is a schematic cross-sectional view through one
embodiment of an implantable self-inflating attenuation device.
[0113] FIG. 48A is side elevational schematic view of a delivery
system for deploying an implantable self-inflating attenuation
device in accordance with one aspect of the present invention.
[0114] FIG. 48B is a cross-section through the line 442-442 in FIG.
48A.
[0115] FIG. 48C is a schematic cross-sectional view through one
embodiment of an implantable self-inflating attenuation device.
[0116] FIG. 48D is an elevated schematic view of a delivery system
for deploying an implantable self-inflating attenuation device in
accordance with one aspect of the present invention.
[0117] FIG. 49 is a schematic representation of an attenuation
device with high vapor pressure media in accordance with one aspect
of the present invention.
[0118] FIG. 50A is a schematic cross-sectional view through a
vessel, illustrating an attenuation device in fluid communication
with the vessel, the attenuation device being in a collapsed
state.
[0119] FIG. 50B is a schematic cross-sectional view through a
vessel, illustrating an attenuation device in proximity to a vessel
with more than one point of pressure communication with the
vessel.
[0120] FIG. 50C is a schematic cross-sectional view through a
vessel, illustrating the attenuation device of FIG. 50A in
proximity to the vessel in an expanded state.
[0121] FIG. 50D is a schematic cross-sectional view through a
vessel, illustrating the attenuation device of FIG. 50B in
proximity to the vessel, the device being in an expanded state.
[0122] FIG. 51A is a schematic cross-sectional view through a
vessel, illustrating an attenuation device that is partially within
and partially outside of the vessel, with a portion of the device
within the vessel expanded.
[0123] FIG. 51B is a schematic cross-sectional view through a
vessel, illustrating the attenuation device of FIG. 51A partially
within and partially outside of the vessel, with a portion of the
device within the vessel in a compressed configuration attenuating
a pressure spike.
DETAILED DESCRIPTION
[0124] Embodiments of the present invention are directed to methods
and apparatus for measuring and/or attenuating and/or baffling
transient and/or cyclical pressure waves in relatively
incompressible materials in organs of the body. Illustrative
embodiments of the present invention discussed herein relate
generally to the fields of cardiovascular medicine, congestive
heart failure, and hypertension. Some embodiments useful in these
fields are discussed herein below, e.g., in connection with FIGS.
17A-17F, 29A-29N, and 50A-51B. However, as will be readily
understood by those skilled in the art, and as described below, the
present invention is not limited to the fields of cardiovascular
medicine, congestive heart failure, or hypertension and apparatus
of embodiments of the present invention may be used in other lumens
and organs of the body as well to attenuate and/or baffle pressure
transients or reversibly occupy intraorgan space. For example, as
discussed in various aspects below, such technology also can be
applied in the fields of urology and gynecology, e.g., in the
treatment of disorders of the urinary tract exacerbated by sudden
fluctuations in intravesical pressure.
[0125] As discussed above, certain embodiments of the present
invention can be deployed to dampen or regulate pressure in the
cardiovascular system. The cardiovascular system consists of the
heart and the vasculature. The vasculature includes a network of
blood vessels that include arteries and veins. The arteries, which
generally convey oxygenated blood away from the heart, are
sometimes collectively referred to as the arterial system. The
veins, which generally convey oxygen poor blood back to the heart,
are sometimes collectively referred to as the venous system. The
heart acts as a pump propelling blood into the arterial system. The
heart propels the blood with each heartbeat. A heartbeat can be
described as having two phases: systole, i.e. when the heart
contracts; and diastole, i.e. when the heart relaxes. The left
ventricle of the heart ejects blood during systole and fills with
blood during diastole. The left ventricle ejects the blood into the
aorta, the largest of the arteries, which acts as a conduit to
carry the blood. The aorta in turn gives rise to arterial branches,
which further serve as conduits for blood flow.
[0126] As the blood is ejected from the heart a pressure wave is
generated within the aorta. The peak of this pressure wave is
referred to as the systolic blood pressure. As the heart relaxes, a
one-way valve (the aortic valve) prevents blood in the aorta from
rushing back into the heart. The lowest blood pressure reached in
the aorta, during the heartbeat cycle, is referred to as the
diastolic blood pressure. The difference between the systolic blood
pressure and the diastolic blood pressure is referred to as the
pulse pressure. Understandably, there is a normal range for these
pressures. An elevation of the systolic and/or the diastolic
pressures above these normal ranges is referred to as
hypertension.
[0127] Hypertension is a common problem that is associated with
cardiovascular disease and stroke. Though there are many causes of
hypertension, primary (or essential) hypertension is responsible
for about 95% of the cases. Systolic blood pressure has become the
predominant concern in hypertensive patients. The determinants of
systolic blood pressure are blood flow, arterial compliance, and
arterial wave propagation. Aging results in arterial stiffening
which causes decreased arterial compliance and subsequent systolic
hypertension. As discussed further below, pressure attenuators
could be used to mitigate peak pressures in a patient's
vasculature. A variety of embodiments of medical devices that can
act as a pressure attenuators, e.g., to modulate high systolic
blood pressure are discussed below. These devices may decrease or
obviate the need for antihypertensive medications.
Five Points about Hypertension [0128] Hypertension, which can be
defined as systolic blood pressure over 140 units or diastolic
blood pressure over 90, is a common problem in Americans. FIG. 1A
illustrates that this problem affects roughly 65 million American
adults. [0129] Hypertension increases in frequency with age, as
illustrated in FIG. 1B. [0130] Hypertension is bad for patients.
Hypertension is a primary risk factor for cardiovascular (CV)
disease and reduction of blood pressure (BP) reduces the risk of
adverse cardiac events and strokes. The relationship between BP and
CV disease risk is continuous, and independent of other risk
factors. [0131] Hypertension is undertreated. Some have estimated
that of those with high blood pressure, 30% are unaware they have
it, 34% are on medication and have it controlled, 25% are on
medication but don't have their high BP under control, 11% are not
on medication. [0132] High Systolic BP has become a predominant
concern in hypertension. Idiopathic hypertension has been estimated
to be responsible for 90 to 95% of patients with hypertension.
[0133] Traditionally, the severity of hypertension was classified
principally on the basis of diastolic blood pressure (DBP) which
was considered to be the best predictor of risk. FIG. 1D
illustrates the relationship between DBP and SBP. However, large
cross-sectional studies have shown that end-organ damage in
hypertensive people is more strongly associated with systolic BP
(SBP) than DBP and recent prospective epidemiologic studies have
directed attention to SBP as a better prognostic guide than DBP in
predicting cardiovascular and all-cause mortality. In fact, DBP
decreases with age. Thus, isolated systolic hypertension (ISH)
becomes the predominant form of hypertension in persons >60
years of age. The relative rise in SBP and fall in DBP results in a
widening of the pulse pressure ((PP); PP=SBP-DBP). Recent data have
underlined the importance of pulse pressure (PP) as an independent
CV risk factor in persons over the age of 50 years. In a
meta-analysis of outcome trials in patients with ISH, the benefit
of treatment was overwhelmingly due to the reduction in SBP rather
than DBP. Also, clinical trials and epidemiologic studies have
shown that control of SBP is more difficult to achieve than control
of DBP.
Determinants of SBP and PP
[0134] The level of SBP results from the interaction of three
principal factors: 1) characteristics of left ventricular ejection
(stroke volume); 2) the cushioning (dampening or compliance)
function of the large arteries (the inverse of arterial stiffness);
and 3) the propagative and reflective properties of the arterial
tree (i.e., intensity of wave reflections and timing of incident
and reflected pressure waves).
[0135] A major role of large arteries is to dampen the pressure
oscillations resulting from cyclic LV ejection of discrete volumes
of blood, which transforms highly pulsatile flow and pressure into
a pattern of more continuous flow in peripheral tissues and organs.
During systole, roughly 40% to 50% of stroke volume is forwarded,
directly to peripheral tissues, whereas the remainder is stored in
the distended aorta and central arteries. Approximately 10% of the
energy produced by the heart is diverted for the distension of
arteries and "stored" in the walls. During diastole, most of the
stored energy causes the aorta to recoil, squeezing the stored
blood forward into the peripheral tissues, thereby favoring more
continuous flow to the peripheral tissues. For the dampening
function to be efficient, the energy necessary for arterial
distension and recoil should be as low as possible. That is, for a
given stroke volume, the SBP and PP should be as low as possible.
See FIG. 1E.
[0136] The relationship between distending pressure and the
corresponding volume change is described in terms of distensibility
(or compliance) or stiffness (or elastance). Stiffness is measured
as the change transmural pressure for a given change in volume of
the vasculature and is expressed as dP/dV (i.e., elastance, where
elastance represents the slope of the pressure-volume relationship
at a specified point on the pressure-volume curve). The
pressure-volume relationship is nonlinear: distensibility decreases
and stiffness increases incrementally at higher BP. That is as the
vessel becomes distended, changes in volume yield larger changes in
pressure. FIG. 1F illustrates a compliance curve for a biological
tissue such as an artery. At low pressures and volumes, compliance
(slope of tangent line) is much greater than at high pressures and
volume. The change in volume for a given change in pressure is
greater at higher compliance. See FIG. 1F.
[0137] A reliable evaluation of arterial stiffness in clinical
practice is based on measurement of pulse wave velocity (PWV) along
a given large artery. PWV is inversely related to distensibility
and directly related to arterial stiffness. The cushioning function
is altered by stiffening (decreased distensibility) of arterial
walls with increased SBP and decreased DBP resulting in high PP as
the principal consequence. See FIG. 1G.
[0138] Arterial stiffening influences SBP and PP by a direct and an
indirect mechanism. The direct mechanism involves the generation of
a higher systolic pressure wave by the left ventricle, which ejects
blood into a stiff arterial system with decreased diastolic recoil
and reduced diastolic pressure. The indirect mechanism acts via the
influence of increased arterial stiffness on PWV and the timing of
incident and reflected pressure waves. The interaction of incident
and reflected pressure waves is the determinant of the final
amplitude and shape of the measured pulse pressure wave at any
point along the arterial tree. With increased arterial stiffening
and increased PWV, reflected waves tend to return earlier to the
central arteries, usually during late systole rather than early
diastole. The result is an augmentation of aortic and left
ventricle pressures during systole, with reduced aortic pressure
during diastole. By favoring early wave reflections, arterial
stiffening contributes to the development of left ventricle
hypertrophy and decreased subendocardial blood flow.
[0139] Arterial stiffening is primarily observed with aging and is
responsible for age-associated increase in SBP. Arterial stiffness
is increased in isolated systolic hypertension in elderly
individuals, in sustained systolic-diastolic hypertension in
middle-aged persons, in patients with type-2 diabetes and in
patients with end-stage renal disease (ESRD). Arterial stiffening
(PWV) and increased wave reflection (augmentation index) are
independent predictors of all-cause and CV mortality in patients
with essential hypertension, in elderly persons, in diabetic
patients, and in ESRD patients. In one technique, augmentation
index is measured as the difference between early and late pressure
peaks divided by pulse pressure.
Pathophysiologic Approach to Reduction of SBP and PP
[0140] Medical treatment of hypertension in younger or middle-aged
individuals usually results in roughly proportional declines in SBP
and DBP. However, in the case of isolated systolic hypertension,
the therapeutic goal is to obtain a preferential decrease of
systolic BP while maintaining unchanged diastolic BP. In the broad
population, however, drug treatment of hypertension more frequently
results in adequate control of DBP than of SBP. Further, patient
noncompliance with medical treatment of hypertension remains high
because of the lack of symptoms in most hypertensive patients. In
total, some estimate that more than 70% of patients with
hypertension are not being properly treated for their high blood
pressure and, therefore, face significantly higher increased risk
for advanced heart and kidney disease and the occurrence of
strokes.
[0141] Considering the different mechanisms associated with
increased SBP, a rational therapeutic approach would reduce
vascular, e.g., arterial stiffness and wave reflection as well as
overall BP. A pressure attenuator in or in proximity to the
arterial system may do just that.
[0142] Another environment in which attenuation of pressure can be
beneficial is the bladder and related body structures. In
particular, certain embodiments of the present invention can be
used to dampen transient intravesical pressure including pressure
spikes experienced by the urinary tract. During a high frequency
transient pressure event, the bladder becomes a relatively
non-compliant environment due to a number of factors including the
pelvic skeletal structure, the compressive loads of contracting
tissues bounding the bladder or the decreased compliance of the
musculature, nerve or connective tissue of the bladder. The factors
contributing to the reduced compliance of the bladder are aging,
anatomic abnormalities or trauma to the structures of the pelvis
and abdomen.
[0143] Urine is primarily composed of water and is virtually
incompressible in the typical pressure ranges present within the
human bladder. The relationship between the maximum urethral
pressure and the intravesical pressure for normal voiding of the
bladder is well defined. With reference to FIG. 1, relaxation of
the urethra occurs before the detrusor muscle contracts to cause
the intravesical pressure 320 to exceed the urethral pressure 322
during normal voiding.
[0144] The bladder serves two mechanical functions: 1) low-pressure
storage and 2) high-pressure voiding. During the storage or filling
phase, the bladder receives an influx of urine from the kidneys.
Compliance of the bladder is defined as the ratio of the change in
volume to the change in pressure, and the static compliance of the
bladder is measured during a typical urodynamic evaluation. The
static compliance index is measured by filling the bladder to
cystometric capacity and allowing the pressures to equilibrate for
a time period of approximately sixty seconds. The static compliance
index is calculated by dividing the bladder capacity by the
Detrusor pressure at the end of filling. A normal bladder will
typically exhibit static compliance between 15 and 30 ml/cm
H.sub.2O. A low static compliance bladder typically will have a
compliance index of less than 10 ml/cm H.sub.2O. With reference to
FIG. 2 which illustrates different pressures for a non-compliant
bladder, a low static compliance bladder typically is poorly
distensible and has a high end-filling pressure. The intravesical
pressure 320 must increase to higher levels to exceed the maximum
urethral pressure 324. The steady state compliance of the bladder
is used to diagnose patients with naturopathic problems such as
damage to the lower motor neurons, upper motor neurons, or multiple
sclerosis. In addition, the steady state compliance of the bladder
is also used, in some cases, to attempt to diagnose problem of
incontinence, including urgency, frequency and cystitis.
[0145] In general, intravesical pressure spikes result from
volumetric tissue displacement in response to gravity, muscular
activity or rapid acceleration. The lack of compliance of the
bladder and the urine contained in the bladder with respect to
events of high frequency, result in minimal fluidic pressure
attenuation of the higher frequency pressure wave(s) and results in
high intravesical pressures that are directly transmitted to the
bladder neck and urethra, which may or may not cause detrusor
contractions. Under these conditions, the urethra may act as a
volumetric pressure relief mechanism allowing a proportional volume
of fluid to escape the bladder, to lower the intravesical pressure
to a tolerable level. The urethra has a maximum urethral pressure
value, and when the intravesical pressure exceeds the maximum
urethral pressure, fluid will escape the bladder. Under these
conditions, nerve receptors in the bladder and/or bladder neck
and/or trigone trigger a detrusor contraction that may lead to
matriculation (frequency) or may subside without matriculation
(urgency) or may lead to the intravesical pressure exceeding the
maximum urethral pressure resulting in fluid escaping the bladder
(incontinence). Under these conditions, waves hitting and/or
expanding the bladder wall, may cause a patient with cystitis to
exhibit significant pain.
[0146] Incontinence is common in males who have undergone radical
prostatectomy, particularly where the sphincter has been
compromised. In these patients, attenuation in the bladder reduces
the intravesical peak pressures, resulting in less urine leakage.
The attenuation requirements in these patients can include short
duration pressure changes--such as, for example, 50 to 400 ms--and
long duration pressure changes--such as, for example, greater than
500 ms--depending on the magnitude of damage to the urinary
sphincter.
[0147] The inventors of the present application have recognized
that for the vast majority of patients suffering from problems of
urinary tract disorders such as frequency, urgency, stress and urge
incontinence and cystitis, the cause and/or contributor to the
bladder dysfunction is a reduction of overall dynamic bladder
compliance rather than steady state bladder compliance. These
patients may often have bladders that are compliant in steady state
conditions, but have become non dynamically compliant when
subjected to external pressure events having a short duration of,
for example, less than 5 seconds or in some cases less than 2
seconds or even less than 0.5 seconds. Reduction in dynamic
compliance of the bladder is often caused by some of the same
conditions as reduction of steady state compliance including aging,
use, distention, childbirth and trauma. The anatomical structure of
the bladder in relation to the diaphragm, stomach, and uterus (for
women) causes external pressure to be exerted on the bladder during
talking, walking, laughing, sitting, moving, turning, and rolling
over.
[0148] The relationship between intravesical pressure 320 and the
maximum urethral pressure 324 for a patient suffering from stress
incontinence due to lack of dynamic compliance in the bladder is
illustrated in FIG. 3. When the patient coughs (or some other
stress event occurs), if the bladder does not have sufficient
dynamic compliance in that frequency range a spike 326 will occur
in the intravesical pressure. Intravesical pressure spikes in
excess of 120 cm H.sub.2O have been urodynamically recorded during
coughing, jumping, laughing or sneezing. When the intravesical
pressure exceeds the maximum urethral pressure value, leakage
occurs. In order to retain urine during an intravesical pressure
spike, the urinary retention resistance of the continent individual
must exceed the pressure spike. Urinary retention resistance can be
simplified as the sum total of the outflow resistance contributions
of the urethra, bladder neck and meatus. In female patients, it is
generally believed that the largest resistance component is
provided by the urethra. One measure of urinary resistance is the
urodynamic measurement of urethral leak pressure. The incontinent
individual typically has a urethral leak pressure less than 80 cm
H.sub.2O. The decline of adequate urinary retention resistance has
been attributed to a number of factors including reduced blood flow
in the pelvic area, decreased tissue elasticity, neurological
disorders, deterioration of urethral muscle tone and tissue
trauma.
[0149] In Practice, the urethral leak point pressure is determined
by filling the bladder with a known amount of fluid and measuring
the intravesical and abdominal pressures when there is a visible
leak from the urethra while the patient is "bearing-down"
(valsalva). With an attenuation device in the bladder, the measured
intravesical leak point pressure typically increases due to the
adsorption of some the abdominal energy by the attenuation device.
In this case, the patient has to push harder to achieve the same
intravesical pressure. Since the abdominal muscles and muscles
surrounding the urethra both contract simultaneously during a
valsalva maneuver, the measured intravesical leak point pressure
and urethral resistance increases when the attenuation device ins
in the bladder.
[0150] Urinary disorders, such as urgency, frequency, otherwise
known as overactive bladder, and interstitial cystitis are caused
or exacerbated when rapid pressure increases or rapid volume
increases or other irritable conditions within the bladder cause
motor neurons to send signals to the brain to begin the cascade of
events necessary for urination. External pressure exerted on the
bladder may result in a detrusor contraction that may result in
urgency, frequency or incontinence. See FIGS. 4A (cough-induced
urgency/frequency) and 4B (non-cough-induced urgency/frequency).
With reference to FIG. 4A, a coughing event 328 induces increased
intravesical pressure 320 which results in increased detrusor
pressure 330. An increase in the detrusor pressure 330 generally is
associated with increased urgency, frequency, or incontinence.
Urinary disorders such as interstitial cystitis or irritable
bladder conditions are a chronic inflammatory condition of the
bladder wall, which includes symptoms of urgency and/or frequency
in addition to pain. Therefore, the problem of a pressure spike in
the functionally noncompliant bladder can be further exacerbated by
a nearly simultaneous contraction of the bladder and a relaxation
of the urethra.
[0151] Certain embodiments of the present invention provide for
methods and devices for measuring and reporting the dynamic
compliance of the bladder. One method of determining dynamic
compliance includes the rapid infusion of a volume of fluid into
the bladder with immediate measurement of the intravesical
pressure. The volume would be more than 50 cc, preferably greater
than 100 cc and more preferably greater than 200 cc. The rate of
infusion would be less than 10 seconds, preferably less than 5
seconds, and more preferably less than 2 seconds. One embodiment of
the present invention includes a two lumen catheter placed within
the bladder, wherein a compliant balloon is rapidly filled with a
non-compliant material, such as saline is infused through one lumen
of the catheter. The resulting intravesical pressure is measured
from the other lumen of the catheter. This infusion can be with a
syringe, a mechanically assisted syringe or pump.
[0152] An additional embodiment provides methods and devices for
treating and/or compensating for reduced dynamic compliance of the
bladder. In one embodiment, a device having a compressible element
is placed within the human urinary bladder, in a manner that allows
the compressible element to act as a pressure accumulator or
attenuator to attenuate transient pressure events. The term
accumulator refers generally to devices that attenuate pressure,
force, or energy in a given locale by absorbing and/or shifting
away said pressure, force, or energy from said locale. The term
attenuator refers generally to devices that attenuate pressure,
force, or energy by dissipating or dampening said pressure, force,
or energy. Gases such as atmospheric air, carbon dioxide and
nitrogen are very compressible in the pressure ranges typically
encountered in the human bladder, and these gases may be used in
attenuation devices inserted in the bladder. Furthermore, when
compared to the tissues encompassing urine, these gases are
significantly more compliant than the immediate environment. The
addition of a proportionately smaller volume of unpressurized gas
acts as a low rate spring in series with the native fluidic circuit
of the urinary tract. Additional information on the basic
scientific principles underlying pressure accumulators and methods
for controlling transient changes in pressure can be found in E.
BENJAMIN WYLIE ET AL., FLUID TRANSIENTS IN SYSTEMS .sctn..sctn.6,
10, 11, 13 (1993); the entirety of these sections are hereby
incorporated by reference herein and made a part of this
specification.
[0153] Accumulators can be designed to keep the pressure from
exceeding a predetermined value or to prevent low pressures.
Accumulators can be designed to protect against rapid transients as
well as against longer-period surges in a system. One example of an
accumulator is a closed container partially filled with the system
liquid and topped with air or gas. The gas may be in contact with
the liquid, in which case an air compressor, or gas supply, is used
to maintain the proper mass of air or gas, or the gas may be
separated from the liquid by a flexible membrane or a piston. The
accumulator generally operates at the local system pressure. With
reference to the embodiment illustrated in FIG. 45, if the valve
302 of the accumulator 300 is closed abruptly the flow 304 enters
the air chamber 306, the air is compressed, and the flow to the
main pipeline 308 is gradually reduced as the pressure builds up,
thereby provides a way to reduce the peak pressure in the chamber
306, the main pipeline 308, and other downstream plumbing and
equipment.
[0154] In one embodiment, shown in FIG. 46, a single accumulator
300 is assumed to have the same pressure throughout its volume at
any given instant. Here, the compressibility of the liquid 310 in
the vessel 312 is considered negligible compared with air
compressibility. Assuming inertia and friction are negligible, the
gas 314 is assumed to follow the reversible polytropic relation
H.sub.AV.sup.n=C.sub.A, where H.sub.A is the absolute head equal to
the gage plus barometric pressure heads, where V.sup.n is the gas
volume 316, where n is the polytropic exponent, and where C.sub.A
is a constant. The exponent n depends on the thermodynamic process
followed by the gas 314 in the vessel 312. If a perfect gas is
assumed, at one extreme the process may be isothermal, n=1, or at
the other limit it may be isentropic, in which case n=1.4 for air.
It should be noted that computation of the aforementioned values,
as well as analogous or related values, can be determined by those
skilled in the art by taking into consideration the foregoing
discussion.
[0155] In another embodiment, the compression of the enclosed
volume of air creates heat that is dissipated into the relatively
infinite heat sink of the body. The balance of the energy absorbed
by the compressed air is simply returned at a different, lower
frequency into the fluidic circuit when the gas is allowed to
expand, as the surrounding tissues return to their initial
positions. The addition of adequate local compliance can
effectively attenuate transient intravesical pressure spikes to
levels below the patient's leak pressure, thus obviating the need
for relief by means of volumetric displacement of urine, and/or
preventing the stimulation of signals to the brain that cause
bladder contractions.
[0156] In accordance with one aspect of the present invention, an
attenuation device is placed within the human urinary bladder. The
attenuation device is intended to be untethered in the bladder and
is intended to remain in the bladder for between several hours and
one year, between one week and six months, or between one and three
months. The attenuation device is a small elastomeric air cell with
a relaxed (unstretched) volume of between 1 and 500 cc, more
preferably between 1 and 100 cc and more preferably still, between
3 and 25 cc. The attenuation device is a unitary component but can
be comprised of two or more subcomponents. The attenuation device
has a substantially uniform wall thickness of between 0.25 inch to
0.0001 inch, more preferably between 0.0005 inch and 0.005 inch,
but could be designed to vary greatly, and still perform the
intended function. In the embodiment described above, attenuation
devices having air cells that are free-floating in the bladder have
been described. In other embodiments of the present invention, air
cells or similar attenuation devices could be surgically affixed to
the bladder wall through the use of suture, staples and other
accepted methods or placed submucosally or intramuscularly within
the bladder wall. Other embodiments could also include attenuation
devices with programmable, variable and adjustable buoyancy by
using ballasting, specific inflation/deflation solutions,
alternative materials of construction or by other means.
[0157] Referring to FIGS. 5 and 5A, there is illustrated one
embodiment of an attenuation device 66 which comprises a moveable
wall such as on an inflatable container 68. The inflatable
container 68 is illustrated as having a generally circular profile,
although other profiles may be utilized in accordance with the
present invention. The diameter of the inflatable container 68 may
be varied within the range of from about 0.25 inches to about 6
inches, in an application of the invention involving the
implantation of only a single attenuation device. Many embodiments
of the inflatable containers 68 will have a diameter within the
range from about 1 inch to about 3 inches, with a total volume
within the ranges recited above. In general, the specific
dimensions and configuration of the inflatable container 68 are
selected to produce an attenuation device having a desired volume
and a desired dynamic compression range, and may be varied from
spherical to relatively flat as will be apparent to those of skill
in the art based upon the disclosure herein. In certain
embodiments, two or three or more discreet inflatable containers 68
are utilized. The sum of the volumes of the multiple containers
will equal the desired uncompressed displacement.
[0158] The inflatable container 68 illustrated in FIGS. 5 and 5A
comprises a flexible wall 70, for separating the compressible
contents of the attenuation device 66 from the external
environment. Flexible wall 70 comprises a first component 74 and
second component 76 bonded together such as by a seam 78. In the
illustrated embodiment, the first component 74 and second component
76 are essentially identical, such that the seam 78 is formed on
the outer periphery of the inflatable container 68. Seam 78 may be
accomplished in any of a variety of manners known in the medical
device bonding arts, such as heat bonding, adhesive bonding,
solvent bonding, RF or laser welding, or others known in the
art.
[0159] The flexible wall 70 formed by a bonded first component 74
and second component 76 define an interior cavity 72. As is
discussed elsewhere herein, interior cavity 72 preferably comprises
a compressible media, such as gas, or foam. Other media or
structures capable of reduction in volume through a mechanism other
than strict compression may also be used. For example, a material
capable of undergoing a phase change from a first, higher volume
phase to a second, lower volume phase under the temperature and
pressure ranges experienced in the bladder may also be used.
[0160] In order to minimize trauma during delivery of the
attenuation device 66, the attenuation device is preferably
expandable from a first, reduced cross-sectional configuration to a
second, enlarged cross-sectional configuration. The attenuation
device 66 may thus be transurethrally deployed into the bladder in
its first configuration, and enlarged to its second configuration
once positioned within the bladder to accomplish the pressure
attenuation function. Preferably, a crossing profile or a greatest
cross-sectional configuration of the attenuation device 66 when in
the first configuration is no greater than about 24 French (8 mm),
and, preferably, no greater than about 18 French (6 mm). This may
be accomplished, for example, by rolling a deflated inflatable
container 68 about a longitudinal axis, while the interior cavity
72 is evacuated.
[0161] Once positioned within the bladder, the interior cavity 72
is filled with the compressible media to produce a functional
attenuation device 66. The present inventors contemplate fill
pressures and volumes of generally less than about 1.5 atmospheres
and 50 ml, respectively, and, in some embodiments, less than 0.5
atmospheres and 25 ml, respectively, such as, for example, in the
case of an air filled collapsible attenuation device 66. In
general, the fill pressure and volume are preferably no more than
necessary to keep the attenuation device 66 inflated in the absence
of pressure spikes. Excessive pressure and volume within the
attenuation device 66 may shorten the dynamic range of the
attenuation device 66, thereby lessening the sensitivity to
attenuate pressure spikes. Pressures of less than 1 atmosphere or
even vacuums may be utilized if the structure of the attenuation
device is sufficient to balance the negative pressure to produce a
net force such that attenuation can occur. This may be
accomplished, for example, in an embodiment where the attenuation
device 66 is provided with a self-expandable support structure
(e.g. nitinol wire frame), which provides a radially outwardly
directed bias.
[0162] The resiliency of the material of the attenuation device,
and the pressure and volume of the inflation media are preferably
matched to produce a compression cycle time which is fast enough to
allow the attenuation device to respond to increases in pressure
while not have a clinically detrimental effect on voiding. For
example, the attenuation device's compression cycle preferably
bottoms out or reaches a maximum in a sufficiently short period of
time as detrusor pressure increases that adverse clinical effects
on voiding are minimized or prevented.
[0163] To facilitate filling the interior cavity 72 following
placement of the attenuation device 66 within the bladder, the
inflatable container 68 is preferably provided with a valve 80. In
the illustrated embodiment, valve 80 is positioned across the seam
78, and may be held in place by the same bonding techniques
utilized to form the seam 78. Valve 80 may be omitted in an
embodiment in which the attenuation device 66 is
self-expandable.
[0164] Valve 80 generally comprises an aperture 82, for receiving a
filling tube therethrough. Aperture 82 is in fluid communication
with the interior cavity 72 by way of a flow path 83. See FIGS. 5
and 7C. At least one closure member 84 is provided for permitting
one way flow through flow path 83. In this manner, a delivery
system and filling device can be utilized to displace closure
member 84 and introduce compressible media into the interior cavity
72. Upon removal of the filling device, the closure member 84
prevents or inhibits the escape of compressible media from the
interior cavity 72 through the flow path 83.
[0165] Thus, the closure member 84 is preferably movable between a
first orientation in which it obstructs effluent flow through the
flow path 83 and a second position in which it permits influent
flow through the flow path 83. Preferably, the closure member 84 is
biased in the first direction. Thus, forward flow may be
accomplished by either mechanically moving the closure member 84
into the second position such as using a filling tube, or by moving
the closure member 84 into the second position by exerting a
sufficient pressure on the compressible media in flow path 83 to
overcome the closure bias. Certain specific valve structures will
be described in connection with FIGS. 8A-E below. However, any of a
wide variety of valve designs may be utilized in the attenuation
device 66 of the present invention as will be apparent to those of
skill in the art in view of the disclosure herein.
[0166] In one embodiment, the attenuation device consists of an air
cell consisting of 0.0018 inch thick polyurethane sheets that have
been bonded together to form a 23/8 inch circle in top view. In one
embodiment, the attenuation device is made from polyurethane and is
intended to be inflated to a pressure slightly above atmospheric
pressure and a volume less than 50 ml or generally within the range
of 0.01 to 1 psi above atmospheric pressure and less than 25 ml.
Integral to the sealing edge 78 of the attenuation device holds a
port/valve 80 utilized in the placement, inflation and release of
the attenuation device. Into the port/valve structure 80 is placed
the distal end of a rigid fill tube (0.050'' OD) 50. The valve 80
employed may be one of the valves described in U.S. Pat. No.
5,144,708, which is incorporated herein by reference. In another
embodiment, the attenuation device may be ultrasonically, radio
frequency, adhesively or heat sealed in situ following inflation,
in which case the valve may be omitted.
[0167] Biocompatible lubricating substances may be used to
facilitate the placement of the attenuation device/fill tube within
the lumen of the introducer. The distal tip of the introducer has
been modified to allow a minimally traumatic presentation of the
attenuation device to the urethral tissue. Biocompatible
lubricating substances may be used to facilitate the insertion of
the attenuation device into the urethra.
[0168] In one embodiment, the attenuation device incorporates
biocompatible coatings or fillers to minimize irritation to the
bladder wall and mucosa and/or to inhibit the formation of mineral
deposits (encrustation). The materials can be coated onto the
surface or incorporated within the wall of the attenuation
device.
[0169] Referring to FIG. 6, there is illustrated one delivery
system for deploying the attenuation device into the treatment
site, such as, for example, the bladder, in accordance with the
present invention. In general, the delivery system 40 is designed
to advance an attenuation device 66 (not illustrated)
transurethrally into the bladder while in a first, reduced
cross-sectional configuration, and to thereafter inflate or enlarge
or permit the expansion of the attenuation device to a second,
implanted orientation. The particular configuration and
functionality of the delivery system 40 will therefore be governed
in large part by the particular design of the attenuation device
66. Thus, as will be apparent to those of skill in the art in view
of the disclosure herein, various modifications and adaptations may
become desirable to the particular delivery system disclosed
herein, depending upon the construction of the corresponding
attenuation device.
[0170] The delivery system 40 comprises an elongate tubular body 42
having a proximal end 44 and a distal end 46. Tubular body 42 is
dimensioned to transurethrally access the bladder. Thus, the
tubular body 42 preferably has an outside diameter of no more than
about 8 mm, and, preferably, no more than about 4 mm. The length of
the tubular body 42 may be varied, depending upon the desired
proximal extension of the delivery system 42 from the urethra
during deployment. In general, an axial length of tubular body 42
within the range of from about 1'' to about 10'' for adult female
patients and from about 4'' to about 30'' for adult male patients
is currently contemplated.
[0171] The tubular body 42 is provided with at least one central
lumen 48 extending axially therethrough. Central lumen 48 axially
slideably receives a filling tube 50, for filling the attenuation
device 66. Filling tube 50 comprises a tubular body 52 having a
proximal end 54 and a distal end 58. An inflation lumen 60 extends
throughout the length of the tubular body 52, and is in fluid
communication with a proximal hub 56. Hub 56 comprises a connector
such as a standard luer connector for coupling to a source of
inflation media.
[0172] The tubular body 52 has an axial length which is
sufficiently longer than the axial length of tubular body 42 to
allow the proximal hub 56 to remain accessible to the clinician and
accomplish the functions of deploying and filling the attenuation
device 66. In one embodiment, an outer tubular sheath (not
illustrated) is slideably carried over the tubular body 42, and is
spaced radially apart from the tubular body 52 to define an annular
cavity for receiving a rolled attenuation device 66 therein. In
this manner, the deflated attenuation device can be rolled around a
distal portion of the tubular body 52 and carried within the
tubular sheath during transurethral placement. Once the delivery
system 40 has been properly positioned, proximal retraction of the
outer sheath with respect to the tubular body 52 exposes the
deflated attenuation device 66. A source of inflation media is
coupled to the proximal hub 56, and media is introduced distally
through central lumen 60 to inflate the attenuation device 66.
Following inflation of the attenuation device 66, the delivery
system 40 is disengaged from the attenuation device 66, such as by
retracting the filling tube 50 with respect to the tubular body 42.
A distal stop surface 47 on tubular body 42 prevents proximal
movement of the attenuation device 66 as the filling tube 50 is
proximally retracted. Delivery system 40 is thereafter removed from
the patient, leaving the inflated attenuation device 66 within the
bladder.
[0173] With reference to FIGS. 6A and 6B, there is illustrated a
modified version of the delivery system 40. In this embodiment, a
control 62 is connected by way of a proximal extension 60 to the
tubular body 52. The control 62 may be in any of a variety of
forms, such as a knob or a pistol grip. The control 62 may be
grasped by the clinician, and utilized to axially advance or
retract the filling tube 50 within the tubular body 42. The
proximal hub 56 is connected to the tubular body 52 by way of a
bifurcation 61. As will be appreciated by those of skill in the
art, the central lumen 60 extends through the bifurcation 61 and to
the proximal hub 56. Proximal extension 60 may comprise a blocked
tubular element or a solid element. An inflation source 64 such as
a syringe filled with a predetermined volume of air or other media
may be connected to the proximal hub 56.
[0174] For patient comfort, the introducer is suitably sized to
easily pass through the urethra (approximately 0.5 to 4 mm
diameter). Visual feedback is provided to the clinician by means of
insertion depth indicators along the longitudinal length of the
introducer. The introducer may also have an adjustable depth stop
that allows the clinician to pre-set the desired insertion depth.
Once the delivery system has been inserted into the urethra to the
desired depth the introducer is then kept in a fixed position and
the attenuation device mounted on the distal end of the fill tube
is then extended in the lumen of the bladder. The attenuation
device is then filled with the indicated volume of gas from the
attached syringe or similar device. See FIGS. 9, 10, 11, and 11A.
Once properly inflated, the attenuation device is released from the
fill tube using the tip of the introducer as an opposing force
disengaging the attenuation device valve from the fill tube. The
fill tube is then retracted completely into the lumen of the
introducer and the entire delivery system is then withdrawn from
the patient. The attenuation device is left in place for the
clinically indicated period of time.
[0175] One aspect of the present invention relates to the delivery
of a very flexible, thin walled device. Delivery of an attenuation
device is typically accomplished via a suitably sized introducer or
possibly through the working channel of an endoscope or cystoscope.
However, in certain instances the columnar strength of an
attenuation device may make it difficult to be pushed through such
channels. A further requirement of any delivery system is that it
be atraumatic, and not pose a threat of tissue damage. This
invention addresses such issues, and offers improvements for
accomplishing delivery of such attenuation devices as disclosed in
U.S. Application Ser. No. 60/197,095, filed Apr. 14, 2000, titled
DEVICES AND METHODS FOR BLADDER PRESSURE ATTENUATION, and U.S.
application Ser. No. 09/723,309, filed Nov. 27, 2000, titled
DEVICES AND METHODS FOR ATTENUATION OF PRESSURE WAVES IN THE BODY,
both of which are incorporated by reference herein in their
entireties.
[0176] The attenuation device is normally folded on itself along
its diameter in order to present a low profile for insertion into,
for example, a patient's bladder transurethrally. In this
configuration the attenuation device has insufficient column
strength to withstand the forces of insertion without buckling. If
the attenuation device buckles it cannot be inserted. Following
insertion the attenuation device is inflated via an inflation tube
to which it is pre-mounted. After inflating the inflation tube is
detached and the attenuation device is freed. By way of
illustration, various embodiments of the invention will be
described in the exemplary context of transurethral insertion of a
delivery system into a patient's bladder.
[0177] In one embodiment, shown in FIGS. 34A and 34B, there is
provided an delivery system for the attenuation device which
consists of an inner fenestrated tubular member which is provided
with an atraumatic rounded tip at its distal end, and an slideably
mounted outer coaxial tubular member. The rounded tip is shaped
such that its proximal end, which is inserted into position in the
distal end of the inner tubular member, presents essentially a
"ramp" designed to aid ejection of the attenuation device from the
fenestration when it is advanced. The attenuation device to be
delivered is attached to its inflation tube, folded as previously
described, and drawn into the inner sheath through the
fenestration. Once situated within the fenestration the outer
coaxial tubular member is slid forward to close the fenestration,
thus containing the bladder within the inner tube.
[0178] With reference to the embodiment illustrated in FIG. 34A,
delivery system 370 comprises an inner sheath 372, a slideable
outer sheath 374, an opening 376 in the inner sheath, and an
atraumatic tip 378. With reference to the embodiment illustrated in
FIG. 34B, delivery system 370 comprises an outer sheath 374 that
slides backwards and an attenuation device 380. Here, the
attenuation device 380 is exposed through the opening 376. The
delivery system 370 comprises an inflation tube 382 that is
advanced toward the atraumatic tip 378, thereby causing the
attenuation device 380 to be ejected. A curved ramp 384 in the
delivery system 370 aids the ejection of the attenuation device
380.
[0179] In use the distal end of the delivery system is inserted
through the urethra to an appropriate depth, the outer coaxial tube
is slid backwards along the inner tube, thus exposing the
fenestration in the inner tube. The attenuation device is advanced
using the inflation tube and releases easily from the inner tube.
The attenuation device is inflated, released from the inflation
tube, and floats freely in the bladder.
[0180] In another embodiment, shown in FIGS. 35A and 35B, the
attenuation device containment tube 386 is a simple open-ended
cylinder. The attenuation device 380 is folded as described
previously and withdrawn into the containment tube 386. The open
end of the containment tube 386 would present a potentially
traumatic edge to the urethra. In order to prevent such trauma, the
open end of the containment tube 386 in this instance has rounded
atraumatic end 378. This end 378 contains slits 388 which, on
sliding the containment tube 386 backwards allow the end 378 to
open, thus allowing deployment of the attenuation device 380 from
the containment tube 386. On advancing the inflation tube 382 with
the attenuation device 380 attached, the slits 388 open and present
little barrier to the deployment of the attenuation device.
[0181] In another embodiment, the attenuation device is delivered
percutaneously through the pelvis into the bladder. Similar to
percutaneous access of arteries or veins, a needle is inserted
through the skin and into the bladder. A guide wire is placed
through the needle and the needle is removed leaving the guide wire
in place. The delivery system and attenuation device are pushed
into the bladder over the guide wire. The attenuation device is
deployed and the delivery system and guide wire are removed.
Guidance using ultrasound can also be employed to help guide the
delivery system into the bladder.
[0182] In one embodiment, a removable delivery system is used to
deliver, deploy, and fill the attenuation device. The delivery
system can take the form of the system taught by U.S. Pat. No.
5,479,945, titled method and a removable device which can be used
for the self-administered treatment of urinary tract infections or
other disorders, issued Jan. 2, 1996, the disclosure of which is
incorporated in its entirety herein by reference.
[0183] With reference to FIGS. 7A and 7B, there is illustrated one
disengagement sequence for deploying the inflatable attenuation
device 66 from the delivery system 40 in accordance with one aspect
of the present invention. As illustrated in FIG. 7A, the delivery
system 40 is initially configured with the filling tube 50
positioned within the valve 80. The distal end 46 of outer tubular
body 42 is dimensioned such that it will not fit through the
aperture 82 of valve 80. Once the attenuation device 66 has been
positioned within the bladder, the attenuation device 66 is
inflated through filling tube 50.
[0184] With reference to FIG. 7B, the filling tube 50 is proximally
retracted following inflation so that it disengages from the valve
80. This is accomplished by obstructing proximal movement of the
attenuation device 66 by stop surface 47 on the distal end 46 of
tubular body 42. The attenuation device 66 is thereafter fully
disengaged from the delivery system 40, and the delivery system 40
may be removed.
[0185] With reference to FIGS. 8A, 32A, and 32B, there is
illustrated a duckbill embodiment of the valve 80. Valve 80
comprises a tubular wall 81, having an aperture 82 in communication
with a flow path 83. At least one closure member 84 is attached to
the tubular wall, and extends across the flow path 83. In the
illustrated embodiment, closure member 84 comprises a first and a
second duck bill valve leaflet 86 and 88 which are attached at
lateral edges 90 and 92 to the tubular wall. The leaflets 86 and 88
incline medially in the distal direction to a pair of coaptive
edges 94 and 96. This configuration allows forward flow through
flow path 83 to separate coaptive edges 94 and 96, thereby enabling
inflation of the attenuation device 66. Upon removal of the
inflation media source, the inflation media within the attenuation
device 66 in combination with natural bias of the leaflets 86 and
88 cause the leaflets to coapt, thereby preventing effluent flow of
inflation media through the flow path 83.
[0186] The tubular body 81 and first and second leaflets 86 and 88
may be manufactured from any of a variety of materials which will
be apparent to those of skill in the art. For example, tubular body
81 may be made from polyurethane such as by extrusion. Leaflets 86
and 88 may be made from any of a variety of flexible materials such
as polyurethane, silicone, or polyethylene, and may be bonded to
the tubular element 81 using adhesives, heat bonding, or other
bonding techniques known in the art. Suitable valves include the
valve manufactured by Target Therapeutics and sold as the DSB
silicon balloon to fill aneurysms and arterial-venous
malformations.
[0187] With continued reference to FIGS. 8A, 32A, and 32B, in one
method of manufacturing the attenuation device 66, the bushing 249
is RF welded to the inflatable container 68 prior to installing the
valve 80. Here, the duckbill valve 80 is bonded to the bushing 249
after welding. In one method of manufacturing the attenuation
device 66, the mandrel is installed during welding, resulting in a
polished surface with an air-tight seal along the inside of the
tube.
[0188] Referring to FIG. 8B, closure is accomplished by two
coaptive edges on distal end 106 of tubular body 81. This
construction is sometimes referred to as a flapper valve. The
tubular body 81 in this embodiment is formed by a first wall 96 and
a second wall 100 which are bonded or folded along a first edge 102
and a second edge 104 to define a flow path 83 extending
therethrough. The free distal ends of first and second walls 96 and
100 at the distal end 106 form coaptive leaflets, which may be
opened under forward flow pressure through the flow path 83 and
will inhibit or prevent reverse flow through the flow path 83.
[0189] Referring to FIG. 8C, the proximal end of the flow path 83
on the flapper valve of FIG. 8B or other valve structure may be
reinforced such as by a reinforcing tube 108. Reinforcing tube 108
may be manufactured in any of a variety of ways. For example,
reinforcing tube 108 may be extruded from various densities of
polyethylene, Pebax, polyurethane, or other materials known in the
art. Reinforcing tube 108 may be desired to maintain patency of the
pathway to the valve 80, particularly in an embodiment adapted for
coupling to a deflation and removal system as will be discussed. In
another embodiment, the reinforcing tube 108 may be removable and
used to prevent sealing of the valve during the manufacturing
process and may also ease the placement of a fill tube in the
valve. This reinforcing tube 108 is removed after the manufacturing
process is complete, or may be removed before, during, or after the
fill tube is placed.
[0190] With reference to FIGS. 8D and 33A, there is illustrated an
additional feature that may additionally be incorporated into any
of the valves discussed above. In one embodiment of this feature,
an annular sealing ring 110 is provided on the interior surface of
the tubular body 81. Annular sealing ring 110 is adapted to provide
a seal with the filling tube 50, to optimize the filling
performance of the attenuation device. Sealing ring 110 is thus
preferably formed from a resilient material such as silicone or
polyurethane and dimensioned to slideably receive the filling tube
50 therethrough. In another embodiment, sealing with the fill tube
may be enhanced by restricting the aperture diameter without the
use of a distinct sealing ring 110. Exemplary dimensions of the
attenuation device 66 are shown in FIG. 33A.
[0191] With reference to FIGS. 8E and 33C, the valve may also be
placed in the body of the attenuation device, rather than in the
seam. In one exemplary embodiment, the through hole 258 has a
diameter of 0.062 inches. Here, the inflation channel 256 has a
diameter of approximately 0.063 to 0.070 inches. The valve can be
placed in any number of ways including the methods described in
U.S. Pat. No. 5,248,275, titled Balloon with flat film valve and
method of manufacture, issued Sep. 28, 1993, and U.S. Pat. No.
5,830,780, titled Self-closing valve structure, issued Nov. 3,
1998; both of these patents are hereby incorporated by reference
herein and made a part of this specification.
[0192] In one embodiment, shown in FIG. 33B, the valve 80 has a
fill/plug 250. In one method of manufacturing the fill/plug
attenuation device 66, the mandrel is installed during welding,
resulting in a polished surface with an air-tight seal along the
inside of the tube.
[0193] The attenuation device 66 is preferably also removable from
the bladder. Removal may be accomplished in any of a variety of
ways, depending upon the construction of the attenuation device.
Preferably, removal is accomplished transurethrally. In one
embodiment, removal is accomplished by reducing the attenuation
device 66 from its second enlarged profile to its first, reduced
profile so that it may be withdrawn transurethrally by a removal
system. The removal system will be configured differently depending
upon whether reduction from the second profile to the first profile
is accomplished by deflation, or by compression. One embodiment of
a removal system utilized to remove an inflatable attenuation
device 66 will be described below in connection with FIG. 12.
[0194] In another embodiment, the removal procedure involves
dissolving or degrading the material or a portion of the material
of the attenuation device 66 in situ. Material selection and wall
thickness of the attenuation device 66 may be optimized to provide
the desired useful life of the attenuation device 66, followed by
dissolution in the aqueous environment of the bladder. In one
embodiment, dissolution or deflation may be catalyzed or
accelerated by an accelerating event such as a change in pH or
introduction of an initiator or accelerator into the bladder, or
reduction of pressure.
[0195] Attenuation devices having a predetermined dwell time after
which they are automatically voided advantageously eliminate the
need for a removal procedure. Such temporary attenuation devices
can be manufactured in a variety of ways in accordance with the
present invention, such as through the use of bioabsorbable or
permeable materials. In one embodiment, the entire wall of the
inflatable container 68 is made from an absorbable material. As
used herein "absorbable" means any material which will dissolve,
degrade, absorb or otherwise dissipate, regardless of the chemical
mechanism, to achieve the purpose recited herein. In another
embodiment, only a portion of the flexible wall 70 or other portion
of the attenuation device such as the valve is made from an
absorbable material. As soon as one or more windows or "fuse"
components of the attenuation device is absorbed, the attenuation
device will deflate through the resulting opening and can be
expelled during normal voiding. In yet another embodiment, one or
more seams such as seam 78 can be bonded by a dissolvable or
absorbable material that is designed to fail after a predetermined
time in the aqueous environment of the bladder.
[0196] The resulting deflated components from any of the foregoing
time limited embodiments can thereafter either be expelled during
normal voiding, or can remain in the bladder in a deflated state
until removed using a removal system. In one embodiment, the
material or portion of the inflatable container 68 is made from a
gas permeable material. As the gas dissipates from the inflatable
container, its ability to spontaneously void increases. In one
embodiment, the attenuation device is filled with approximately 20
ml of gas and the attenuation device's material allows
approximately 15 ml of gas to permeate out of the attenuation
device over certain time intervals, such as, for example, one,
three, six, or twelve months. Once the volume remaining is less
than approximately 5 ml, the attenuation device is normally
voided.
[0197] The predetermined dwell time within the bladder can be
influenced by a variety of design factors, including the
formulation of the absorbable material and the physical shape,
thickness and surface area of the absorbable component. A variety
of absorbable polymers which can be used in the present invention
are known in the absorbable suture arts. For example, absorbable
multifilament sutures such as DEXON sutures (made from glycolide
homopolymer and commercially available from Davis & Geck,
Danbury, Conn.), VICRYL sutures (made from a copolymer of glycolide
and lactide and commercially available from Ethicon, Inc.,
Somerville, N.J., and POLYSORB sutures (also made from a copolymer
of glycolide and lactide and commercially available from United
States Surgical Corporation, Norwalk, Conn.) exemplify materials
known in the industry and characterized as short term absorbable
sutures. The classification short term absorbable sutures generally
refers to surgical sutures which retain at least about 20% of their
original strength at three weeks after implantation, with the
suture mass being essentially absorbed in the body within about 60
to 90 days post implantation.
[0198] Certain bioabsorbable elastomers may also be used to form
the attenuation devices or fuses in accordance with the present
invention. The elastomers can be melt-processed, for example by
extrusion to prepare sheets, plugs or tubular structures. In one
embodiment, the copolymers can be injection molded to fabricate
intricately designed parts, or compression molded to prepare films.
For the details of such melt-processing techniques, see, for
example, F. Rodriguez, Principles of Polymer Systems, Chapter 12
(McGraw Hill 1970).
[0199] The bioabsorbable elastomers can also be solvent cast to
prepare thin films. Solvent casting can be accomplished using
conventional methods such as first dissolving the copolymer in a
suitable solvent to make a solution, then casting the solution on a
glass plate to make a film, and then evaporating the solvent from
the cast film. In another processing scheme, the copolymers can be
lyophilized to prepare foams. Lyophilization can be accomplished by
first dissolving the copolymer in an appropriate solvent, freezing
the solution, and then removing the solvent under vacuum. The set
of appropriate solvents include p-dioxane. Lyophilization
techniques to prepare films are described in Louis Rey, Aspects
Theoriques Et Industriels De La Lyophilization (1964).
[0200] Certain bioabsorbable elastomers are disclosed in U.S. Pat.
No. 6,113,624, titled Absorbable elastomeric polymer, issued Sep.
5, 2000, the disclosure of which is incorporated in its entirety
herein by reference. In accordance with the process disclosed
therein, a two-step, one-reaction vessel, two-temperature process
is utilized in which a mixture of p-dioxanone monomer and
p-dioxanone homopolymer, is formed at low temperatures of from
about 100.degree. C. to about 130.degree. C., preferably
110.degree. C. The mixture is then reacted with lactide at
temperatures from about 120.degree. C. to about 190.degree. C. to
form copolymers in which segments or sequences are composed of both
p-dioxanone and lactide repeating units. These segmented copolymers
are stated to be less crystalline than the block or graft
copolymers previously known in the art and, therefore, yield
materials with good strength, but shorter BSR ("Breaking Strength
Retention") profiles, faster absorption rates, much longer
elongations and lower stiffness than the block copolymers. A wide
variety of copolymers of polylactic and polyglycolic acids are also
known in the art, particularly for use with absorbable orthopedic
screws and fasteners.
[0201] The ideal material can be optimized through routine
experimentation taking into account the attenuation device design
and the desired indwelling time period. Attenuation devices may be
time rated, such as 15 days, 30 days, 45 days, 90 days, 180 days or
other as may be desired. The deflated and/or partially dissolved
attenuation device will be transurethrally expelled within a few
days of the expiration of the rated time period from the time of
implantation.
[0202] Referring to FIG. 12, there is illustrated a side
elevational schematic view of one embodiment of an intravesical
removal system in accordance with the present invention. This
removal system is adapted to retrieve the inflatable attenuation
device discussed elsewhere herein. The removal system 150 comprises
an elongate tubular body 152 which extends between a proximal end
154 and a distal end 156. Tubular body 152 is dimensioned to
transurethrally access the bladder. In one embodiment, the removal
system 150 is adapted for use in conjunction with standard
urological cystoscopes (e.g. approximately 14-24 French), having
minimum working channels of approximately 1.8 to 6.0 mm. For this
purpose, removal system 150 in one embodiment has an overall length
of approximately 76 cm and a useable length of approximately 60
cm.
[0203] The tubular body 152 may be manufactured in accordance with
any of a variety of techniques well understood in the catheter and
other medical device manufacturing arts. In one embodiment, tubular
body 152 is extruded from a biocompatible material such as `114E,
having an inside diameter of approximately 0.09 inches and a wall
thickness of about 0.01 inches.
[0204] The proximal end 154 of tubular body 152 is connected to a
Y-adaptor 158. Y-adaptor 158 carries a control 160 for controlling
the retrieval system as will be described. Control 160 in the
illustrated embodiment comprises a thumb ring 162 which is
slideably carried with respect to a pair of finger rings 164. Axial
movement of the thumb ring 162 with respect to the finger rings 164
enlarges or retracts a retrieval loop 166 extending distally from
distal end 156 of tubular body 152. Retrieval loop 166 is adapted
to surround the inflated attenuation device 66. In one embodiment,
the loop 166 has an enlarged diameter of about 27 mm, and comprises
a wire such as 0.016 inch diameter stainless steel cable wire.
[0205] In use, the loop 166 is opened once the distal end 156 of
the tubular body 152 has reached the bladder. The loop 166 is
positioned around the attenuation device 66, and the proximal
control 160 is manipulated to tighten the loop 166 around the
attenuation device 66. After the attenuation device 66 has been
securely grasped by the loop 166, a deflating tube 168, preferably
having a sharpened distal tip 169 thereon, is distally advanced
through the wall of the attenuation device 66. Distal advancement
of the deflating tube 168 may be accomplished by distally advancing
a proximal control, such as control 172. The distal tip 169 is in
fluid communication with a connector such as a standard luer
adaptor 170 through a central lumen (not illustrated), so that an
empty syringe or other device may be connected to the connector 170
and used to evacuate the contents of the ensnared attenuation
device 66. As the attenuation device 66 is deflated, the control
160 may be manipulated to pull the collapsed attenuation device 66
into the distal end 156 of the tubular body 152. The removal system
150 having the reduced attenuation device 66 therein or carried
thereby may be transurethrally removed from the patient.
[0206] A wide variety of modifications can be made to the foregoing
removal system 150, within the spirit of the present invention. For
example, the proximal controls 160 and 172 may be combined into a
pistol grip or other configuration. Controller 172 or control 160
may additionally control deflection of the distal end 156 of the
tubular body 152, or control rotation of the plane of the loop 166.
In general, the removal system 150 preferably accomplishes the
basic functions of enabling the location of the attenuation device
66, capturing the attenuation device, reducing the attenuation
device in size and removing the attenuation device from the
bladder. The capturing step may be accomplished by visualizing the
attenuation device through the urological cystoscope, or by "blind"
techniques, such as, for example, light reflectance, impedance,
suction, ultrasound, passive induced microchip, or the magnetic
locator described in connection with FIGS. 21, 22, 23, below.
[0207] Referring to FIGS. 13 and 13A, there is illustrated a top
plan view of one embodiment of an attenuation device 180 in
accordance with one aspect of the present invention. The
attenuation device 180 comprises an inflatable body 68 generally as
has been described. An outer seam 78 may be provided with a valve
80. In this embodiment, an inner seam 182 defines a central region
184. The outer seam 78 and inner seam 182 define a generally
toroidal-shaped inflatable container 68. The central region 184 may
comprise either a membrane or a central opening, depending upon the
desired performance characteristics. The center hole may assist in
the placement and location of the attenuation device within the
bladder, permit additional baffling of the pressure waves within
the bladder, minimize the attachment to the bladder wall by surface
tension between the attenuation device and the bladder wall, and
allow for urine flow through the hole in the event that the
attenuation device is in or near the bladder neck.
[0208] In one embodiment, illustrated in FIGS. 14 and 14A, the
central region 184 comprises a baffle 186. The baffle 186 comprises
a membrane 188 having a plurality of apertures 190 therein. In the
illustrated embodiment, approximately nine round apertures 190 are
provided, each having a diameter of about 0.2 inches. Generally at
least about 9 apertures 190 are provided, and many embodiments
include anywhere from about 1 to about 1000 apertures. The optimal
number of apertures 190 and sum of the area of the apertures 190
compared to the total area of the baffle 186 may be optimized
depending upon the desired performance characteristics. Apertures
may have any of a variety of configurations, such as round holes,
irregular openings, slits or others.
[0209] The wave diffuser function of the baffle 186 is
schematically illustrated in FIG. 15. A wave front 192 may be
generated by any of a wide variety of events, such as coughing,
sneezing, laughing, physical movement, muscle spasms or others as
is understood. Since urine comprises essentially non-compressible
water, and due to the low dynamic compliance of the bladder the
wave front 192 will propagate rapidly through the bladder to impact
structures such as the trigone area and the urethra. Apparent
transient pressure spikes as high as 80 cm H.sub.2O or greater can
be experienced during normal activities. In addition to reducing
the pressure caused by pressure events such as coughing, the
attenuation devices discussed above can also provide a baffle that
distributes the wave across the bladder distributing and reducing
the focused wave front that contacts the bladder neck.
[0210] If the attenuation device 180, having a baffle 186 is
positioned within the bladder, the baffle 186 functions to disrupt
the unitary progression of the wavefront 192. The prediffusion wave
front 192 is thus interrupted into a plurality of post-diffusion
wave fronts 194 by the baffle 186. Although the sum of the
resulting post-diffusion wave fronts 194 is essentially equal to
the prediffusion wave front 192, the greater dispersion of force
accomplished by the baffle 186 is believed by the inventors to
reduce the apparent magnitude of the wave front 192 as experienced
by target tissue within the bladder.
[0211] As will be apparent in view of the foregoing, the baffle 186
may be constructed in any of a variety of manners and still
accomplish the intended result. Thus, although the attenuation
device 180 illustrated in FIGS. 13 and 14 comprises a generally
toroidal-shaped inflatable container, any of a variety of other
support structures may be utilized to maintain the baffle 186 in a
useable configuration. The support 196 can comprise an inflatable
tube, a resilient material such as nitinol wire, or other support
structure as may be desired.
[0212] Certain embodiments of the present invention include a
device that is mechanically in contact with the mucosal surface or
tissue of the bladder or urethra. The sensation caused by the
mechanical contact causes nerve receptors to tighten the urethral
muscles increasing urethral resistance, thus, reducing or
eliminating incontinence events.
[0213] Referring to FIG. 16, there is illustrated a variety of
shapes for the attenuation device 66, of the inflatable container
variety. The devices used in embodiments of the present invention
may take many shapes. In some instances it may be desirable for
manufacturing purposes to have the shape resemble dip-molded
devices like condoms, surgical glove fingers, or children's toys.
However, many other forms may provide better performance, in
particular for providing baffling of pressure waves as well as
attenuation of pressure spikes. Possible shapes for the attenuation
devices include toroid like shapes, similar in form but not size to
donuts and inner tubes; spoked wheel forms; horseshoe-like forms;
mushroom-like forms; and banana-like forms.
[0214] The attenuation devices of the present invention can be dip
molded or extruded in a plurality of biocompatible materials.
Furthermore, the attenuation devices can be fabricated from a
variety of multi-layer composites or produced by a number of
different manufacturing processes. Here, the designs of the
attenuation devices are characterized by minimization and control
of the gas and moisture vapor permeabilities in and out of the
attenuation device.
[0215] The gas and moisture vapor permeabilities of any given
material will vary depending on the conditions surrounding the
material. For example, an attenuation device comprised of a certain
material can have different gas and/or moisture permeabilities
within the bladder than at standard temperature and pressure. In
addition to exposure to urine, the intravesical environment
includes exposure to pressure variations in the range of from about
0.05 psi to about 0.25 psi at rest, with transient pressure spikes
as high as 2 psi or more. The body temperature is normally about 98
degrees F. or greater, and the attenuation device resides in 100%
humidity. Long term efficacy of the attenuation device may be
compromised if there exists any fluid or vapor exchange through the
wall of the attenuation device in situ. The relative impermeability
of the wall under normal intravesical conditions is preferably
accomplished without losing the compliancy of the attenuation
device which allows it to compress within folds of the bladder as
is described elsewhere herein.
[0216] In general, the wall of the attenuation device will comprise
at least one gas barrier layer and at least one moisture barrier
layer. Any of a variety of gas barrier materials (e.g.
polyvinylidene chloride, ethyl vinyl alcohol, fluoropolymers,
etc.), available in thin film constructions, may be implemented
into the attenuation device design. These materials are generally
relatively stiff, have a high moisture vapor permeability, and have
low impact strength. Consequently, layering the film with flexible,
high moisture barrier, high impact strength polymers is
desirable.
[0217] A variety of relatively flexible materials, having high
moisture barrier characteristic and optionally high impact strength
that can be formed into thin film sheets include but are not
limited to: polyamide, polyethylene, polypropylene, polyurethane,
polyamide/polyester copolymer, polystyrene/polybutadiene copolymer,
etc. In one embodiment, at least one layer on, or the entire
attenuation device comprises a blend of a barrier material and a
flexible high impact strength material (e.g.
polyurethane/polyvinylidene chloride, polyethylene/ethyl vinyl
alcohol, etc.).
[0218] The attenuation device typically has two or more layers or
barriers. For example, the attenuation device can have a gas
barrier layer and a moisture barrier layer. An additional layer may
be included to enhance the structural integrity of the attenuation
device. In one embodiment, the attenuation device has an outer
layer comprising a gas barrier and an inner layer comprising a
moisture barrier. In another embodiment, the attenuation device has
an outer layer comprising a moisture barrier and an inner layer
comprising a gas barrier.
[0219] The attenuation device can have three, four, five, or more
layers. In one embodiment, the attenuation device has a gas barrier
layer, a moisture barrier layer, and one or more layers composed of
at least one high impact strength material. In another embodiment,
the attenuation device has multiple gas barrier layers arranged in
a nonconsecutive arrangement. In yet another embodiment, the
attenuation device has multiple moisture barrier layers arranged in
a nonconsecutive arrangement. With respect to those embodiments
having multiple, nonconsecutive barrier layers, the other layers of
the attenuation device can include high impact strength material
layers and/or other types of barrier layers.
[0220] The overall thickness of the wall is preferably minimized,
and will often be no more than about 0.03 inches. Preferably, the
wall will be no more than about 0.006 inches, and, in some
implementations, is no more than about 0.003 inches thick. An outer
layer may comprise a soft, conformable material such as
polyurethane, EVA, PE, polypropylene, silicone or others, having a
thickness within the range of from about 0.0025 inches to about
0.025 inches. The adjacent barrier layer may comprise EVOH, PVDC or
other materials in a thin film such as from about 5 microns to
about 25 or 30 microns thick. If the attenuation device is
fabricated by bonding two sides together, a bonding or tie layer
may be provided on the barrier layer. Tie layers comprising
polyurethane, EVA or others may be used, having a thickness of
preferably no greater than about 0.001 inches. Layers of less than
about 0.0008 are preferred, and layer thicknesses on the order of
from about 0.0003 to about 0.0005 inches are contemplated.
[0221] The layers of the attenuation device can be formed in any
number of ways known to those skilled in the art, including, but
not limited to, lamination, coextrusion, dip molding, spray
molding, or the like, etc. As discussed above, the layers of the
attenuation device can be formed from various materials. With
respect to those attenuation devices that are formed by laminating
two or more layers together, various different laminating
techniques known to those skilled in art can be used, including,
but not limited to, heating, solvents, adhesives, tie layers, or
the like.
[0222] The material may not need to be elastomeric at all for the
attenuation device to function. However, the materials chosen for
use in embodiments of the present invention are to be sufficiently
flexible in the thickness ranges dictated by the selected designs.
When the attenuation device is subjected to external pressures, the
attenuation device's material is able to transmit the pressure to
the contained air or pressure management construct and respond
sacrificially as one of the most compliant members of the urinary
system.
[0223] FIG. 16A illustrates a toroidal embodiment, in which a
plurality of central spokes is provided. FIG. 16B illustrates a
crescent or "C" shaped attenuation device. Any of a variety of
spherical, oval, elliptical or other shapes may be utilized such as
those illustrated in FIG. 16C, in which the greatest length
dimension of the inflated attenuation device is within the range of
from about 1 to about 5 times the smallest cross-section. FIG. 16D
illustrates a less arcuate variety as shown in FIG. 16B. In
general, the attenuation device 66 may take any of a variety of
forms which provides a sufficient volume to achieve the desired
attenuation function, and which will minimize or eliminate risk of
loss or obstructing outflow through the urethra.
[0224] Referring to FIGS. 17A-17B, there is illustrated a
bellow-type attenuation device 200 in accordance with one
embodiment of the present invention. FIGS. 17C-17F illustrate one
environment in which the attenuation device 700 can be used.
[0225] The bellow 200 may be compressible to provide attenuation,
as discussed further below. The compressibility of the bellow 200
may be provided by a suitable mechanical structure or mechanism.
For example, in one arrangement, a mechanism or mechanical
structure is provided that enables the device to be axially
compressible. In one arrangement, the bellow 200 comprises a
membrane 202 that surrounds a volume. The membrane 202 may be
self-supporting. The membrane 202 may be configured to be
collapsible, such as in an accordion fashion. In some embodiments,
a support structure such as a frame is provided. The frame or other
support structure may be located on the inside of the membrane 202,
e.g., within the volume defined therein, or external of the
membrane. In some arrangements, a support structure is located in
part inside a volume defined within the membrane 202 and in part
outside the membrane. For example, a first portion of a support
structure may be provided to maintain, at least in part, the
external shape of the bellow 200 and a second portion may be
provided for coupling the bellow device 200 to a vessel, as
discussed further below.
[0226] Where provided, the support structure may comprise any of a
variety of features, such as a simple spring aligned in parallel
with (or configured to direct a restoring force along) a
longitudinal axis of the bellow 200. Where provided, a support
structure can comprise a pivotally moveable structure, such as an
axially compressible wire pantograph, as will be understood in the
art. Any of these and other mechanical structures can be located
internally or externally to the membrane 202.
[0227] Various embodiments of attenuation devices for absorbing
transient pressure changes or spikes may include one or more of
diaphragmatic structures, rigid, or deformable structures (e.g.,
capable of changing shape). Attenuation devices for absorbing
transient pressure spikes can be configured with a coating or
covering that can dampen pressure waves in an organ or vessel.
Attenuation devices for absorbing transient pressure spikes can
include a bellow or bellow-like structure that can dampen pressure
waves in an organ, chamber or cavity of the body, as discussed
above. These embodiments can be configured as stand alone
attenuation devices or as part of the wall or structure of the
organ or vessel of interest, as discussed further below.
[0228] As discussed above, the bellow 200 is one form of a
mechanically assisted attenuation device. The bellow 200 can be
configured to relax to the extended position of FIG. 17A when at
rest. In one arrangement, the extended position of FIG. 17A is a
first state which occupies a first volume. The bellow 200 can be
configured to relax to the extended position when not subject to a
pressure above a selected level. Such a selected level is sometimes
referred to herein as an activation level or an activation
pressure. The activation level may be a threshold level. In some
vascular applications, the activation level may be a level above
which a risk of stroke, aneurysm or other deleterious
cardiovascular event is appreciable. Such a level may depend at
least in part on criteria of the patient. For example, for
relatively young patients, the activation level may be a value of
systolic pressure outside the range of normal systolic pressures
that the patient might experience under a normal range of
activities. For relatively old patients, the activation level might
be selected to be within the range of systolic pressures that the
patient could expect to experience under a normal range of
activities. An activation level within a normal range could be
selected to reduce the risk of a deleterious event, such as a
stroke, where there are other risk factors, such as thinning or
brittle vasculature. In other vascular applications, the activation
level may be a level below which a vascular event is
appreciable.
[0229] The bellow 200 can be configured such that the tendency
thereof to expand to the position shown in FIG. 17A is balanced.
For example, the pressure within the bellow 200 can be reduced such
that the bellows normally retains its extended position, but will
compress when an external pressure of a selected magnitude (e.g.,
at or exceeding the activation pressure) is exerted on it. The
bellow 200 may be sealed, or covered in a material that allows for
reduction of the pressure within the structure.
[0230] FIG. 17B illustrates a second state of the bellow 200. In
particular, a portion of the bellow 200, such as an attenuation
zone 203 thereof, can be compressed so that the bellow occupies
less volume than in the first state. As discussed herein this
response can attenuate pressure in an anatomical structure in which
the bellow 200 may be placed. Accordingly, the bellow 200 can be
used to attenuate pressure spikes that are in a range that can
arise in a human body, e.g., physiologic pressure spikes.
[0231] The bellow 200 could be made from any suitable material,
including a polymeric film or a metal, such as, for example,
titanium or stainless steel. The bellow 200 could be made from a
combination of these or other suitable materials. Senior
Flextronics, Inc. of Sharon, Mass. is one source for such
materials.
[0232] One advantage of a mechanical attenuator such as the bellow
200 is that a large change of volume occupied by the bellow can be
achieved, in response to a relatively small pressure rise beyond
the present threshold. The change of volume of evacuated mechanical
attenuators can be significantly greater than that achieved in
devices that enclose or include a compressible medium. For example,
an air or gas cell similar to those described herein might be able
to be reduced by approximately 25% of its volume. Some mechanical
attenuators can be reduced by at least about 30%, sometimes at
least about 50% and in some implementations at least about 90% of
its volume.
[0233] FIGS. 17C and 17D illustrate that the bellow 200 can be
placed within the cardiovascular system. In particular, the bellow
200 is shown positioned in an aorta A, just above the bifurcation
distal of the iliac arteries. FIG. 17C illustrates that the bellow
200 can be configured to be in a first, extended state when placed
in a blood vessel. FIG. 17D illustrates the response of the bellow
200 to a physiologic pressure spike. In particular, the bellow 200
is shown moved from the first state to a second, compressed state.
The second state occupies less volume than the first state. Because
the bellow 200 occupies less volume, more volume within the vessel
is available for blood. The difference in volume between the first
and second states preferably is sufficient to alleviate at least
one cardiovascular malady, such as excessive systolic pressure. In
some applications, the difference in volume between the first and
second states is sufficient to reduce a pressure spike within the
vasculature.
[0234] Referring to FIGS. 17E and 17F, the bellow 200 can be placed
in proximity to or in pressure communication with the vasculature.
In this arrangement, a container 206 is provided in which the
bellow 200 or other attenuator can be contained or mounted. In one
arrangement, the container 206 comprises a connection zone 207 for
connecting the bellow 200 to a blood vessel. The container 206 can
be sutured or otherwise affixed to the vasculature. The container
206 and the bellow 200 can be coupled together in any suitable
manner. In one arrangement, a portal or opening is provided between
the container 206 and the vasculature such that blood is in fluid
communication with the bellow 200. In another arrangement, the
container 206 and the bellow 200 are in pressure communication with
the vasculature without requiring fluid communication between the
portion of the container housing the bellow 200 (e.g., an inside
volume of the container 206) and the vasculature. Where the bellow
200 is in fluid communication with the vasculature, any suitable
technique may be used to maintain flow into the container 206, such
as providing suitable anticoagulation therapy. The bellow 200 and
the other implantable blood pressure regulators can be combined
with another treatment, such as a pharmaceutical therapy, to manage
a cardiovascular malady, as discussed further below.
[0235] Although FIGS. 17C-17F illustrate the bellow 200 in pressure
and in fluid communication with a patient's aorta, the bellow
device and other pressure regulators disclosed herein can be
applied to other vessels through the vasculature.
[0236] Referring to FIG. 18, there is illustrated a
mechanically-assisted attenuation device 210 in accordance with the
present invention. In this embodiment, a compressible tubular wall
212 having closed ends 214, 216 is supported by a self-expanding
tubular frame 218. Any of a variety of self-expanding tubular or
spherical frame structures may be utilized, such as "zigzag" wire
frames well known in the abdominal aortic aneurysm graft arts.
Although the abdominal aortic aneurysm graft application generally
requires a relatively high, radially outwardly directed force, the
present application would preferably be compressible with a
relatively low compressive force (i.e., low radial force). This may
be accomplished by using wires of smaller gauge, less wire per
graft, leaving adjacent apexes unconnected to each other, or other
technique to reduce the radial force of the wire cage. The wire
cage or other support structure is preferably surrounded by a water
impermeable membrane such as a balloon. Pressure within such
balloon may be lower than 1 atm.
[0237] Referring to FIGS. 19A and 19B, there is illustrated another
layout for the inflatable attenuation device 66 of the present
invention. In this embodiment, illustrated in FIG. 19A, a plurality
of attenuation devices 67 are connected by a common flow path 65,
so that the plurality of attenuation devices 67 can be inflated
through a single fill port. In another embodiment, illustrated in
FIG. 19B, a plurality of self-expanding attenuation devices are
connected by a suture, Nitinol wire, or other tether, thereby
minimizing the crossing profile and/or maintaining a constant
crossing profile for an attenuation device of any desired total
inflated volume.
[0238] FIGS. 20-23 illustrate a magnetic locating system for
enabling "blind" retrieval without the use of a cystoscope. To
remove the attenuation device from the bladder, the removal system
is inserted into the urethra for intravesical capture, deflation,
and extraction of the attenuation device. The removal system
utilizes a magnet whose polarity and flux path is oriented in a
manner to ensure predictable attraction and coupling of a
magnet-containing attenuation device to the removal system. The
removal system is coupled back to the attenuation device, and the
attenuation device may be punctured and deflated using the jaws of
biopsy-like forceps (or other solution suitable for deconstructing
the device) located at the distal end of the removal system. In one
embodiment, residual gas may be passively vented into the bladder
or through the retriever body. Once deflated the attenuation device
may be withdrawn through the urethra attached to the removal system
or allowed to pass out of the bladder as part of the urine
flow.
[0239] Thus, referring to FIG. 20, there is illustrated an
attenuation device 230 such as an inflatable balloon 229 as has
been described previously herein. The attenuation device 230 is
provided with a valve 232 and a locating element 234. Locating
element 234 may be any of the variety of structures which enable
location of the attenuation device 230, preferably without the need
for direct visualization.
[0240] In the illustrated embodiment, the locating element 234 is
one or more magnets 236. In the embodiment illustrated in FIG. 21,
the magnet 236 comprises an annular ring, for surrounding the flow
path 83. A corresponding magnet 238 having reversed polarities from
the polarity of the magnet 236 is provided on the distal end of a
catheter 240. The attractive forces of the opposing polarity
magnets 236 and 238 will cause the catheter 240 to couple on to the
attenuation device 230, as illustrated in FIG. 22, when the
catheter 240 is positioned in the vicinity of the attenuation
device 230.
[0241] Referring to FIG. 22, at least one lumen 242 places the
attenuation device 230 in fluid communication with the catheter 240
when the locating element 234 is coupled to the catheter 240. This
lumen 242 may be utilized to either introduce inflation media or
remove inflation media from the attenuation device 230. In FIG. 22,
the valve 232 is a ball valve, which is biased in the closed
orientation. However, the mechanism and structures disclosed herein
may be used on any of the other valves disclosed elsewhere herein.
In one embodiment, illustrated in FIG. 22, a valve actuator 234 may
be advanced distally through the lumen 242 to displace the valve
232 and enable infusion or removal of inflation media. Following
the desired volume of infusion or removal of inflation media, the
valve actuator 234 may be proximally retracted, to enable the valve
to close under its own bias. See FIG. 23.
[0242] The opposing magnets 236 and 238 may be utilized solely as a
locating structure, such that an additional locking element (not
illustrated) may be utilized to lock the catheter 240 on to the
attenuation device 230. This may be desirable if the strength of
the bond formed between the two magnets is insufficient to keep the
attenuation device 230 coupled to the catheter 240 during the
filling or removal steps. In addition, following deflation of the
attenuation device 230, the catheter 240 will generally require a
relatively strong coupling to the attenuation device 230 to
retrieve the attenuation device 230, as will be apparent to those
of skill in the art in view of the disclosure herein.
[0243] In accordance with one aspect of the present invention, the
removal system is provided with one or more ultrasound transducers
near a distal end thereof. An air filled attenuation device should
strongly reflect an ultrasound signal, in a manner similar to the
reflection achieved at an air-water interface. A removal system
provided with a deflectable distal tip and ultrasonic capabilities
should be able to navigate through the bladder to locate an
attenuation device without the need for visualization. The removal
system may additionally be provided with a grasping element, such
as two or more opposing mechanical graspers, and/or a vacuum lumen,
for attaching to the surface of the attenuation device using
suction. Once attached, the attenuation device can be pierced and
transurethrally withdrawn.
[0244] In accordance with another aspect of the present invention,
there is provided an attenuation device that may assume multiple
shapes during the course of its use. For example, the attenuation
device may be completely deflated for introduction and inflated to
varying degrees after introduction. The attenuation device may be
adjusted through the inflation/deflation of secondary or multiple
containment cells for such purposes as ballasting or the addition
of a diagnostic, therapeutic or signaling substance. This may occur
through multiple uses of a single, or single uses of a multi lumen,
multi ported structure or combinations thereof.
[0245] In accordance with another aspect of the present invention,
the delivery system and the removal system of the attenuation
device or accumulator are two separate instruments. In another
embodiment, the delivery system and the removal system are
implemented using a single instrument. In yet another embodiment
there is provided one instrument having different distal ends for
the delivery system and the removal system.
[0246] In accordance with another aspect of the present invention,
an endoscope may be used to launch and retrieve the device (i.e.
attenuation device, accumulator, etc.).
[0247] In accordance with another aspect of the present invention,
the distal tip of the delivery system may be straight, pre-curved,
malleable, or steerable (e.g., by pull wires) in order to
facilitate delivery and/or release of the device.
[0248] In accordance with another aspect of the present invention,
the separation of the attenuation device from the fill tube may be
accomplished using the wall of the urethra or neck of the bladder
as a mechanically resistant body.
[0249] In accordance with another aspect of the present invention,
the delivery system may consist of a single tubular element, a
series of concentric tubular elements, a series of non-concentric
tubular elements, an extruded element, a spirally wound guidewire
element, or any combination of the aforementioned elements arranged
in a manner to provide the desired functions.
[0250] In accordance with another aspect of the present invention,
irritation concerns are addressed through the use of coatings or
fillers to physically or chemically modify the attenuation device
in whole or part in order to modulate characteristics such as
lubricity and the ability to inhibit the deposition of materials
present in the urinary tract. For example, substances such as
sulfated polysaccharides may be used before, during, or after
introduction to the patient. In addition, the use of a plurality of
construction materials with unique surface properties may also be
used for this purpose.
[0251] In accordance with another aspect of the present invention,
the attenuation device includes a portal that spans the distance
from the internal aspect to the external aspect that allows for the
location of an erodible substance that would allow for the
deflation or deconstruction of the attenuation device after
exposure to urinary tract conditions for a prescribed period of
time. This approach may also be used for the programmed bolus
release of single or multiple therapeutic, diagnostic or signaling
substances from single or multiple chambers within the attenuation
device.
[0252] In accordance with another aspect of the present invention,
the attenuation device is equipped with a valve/port that is
programmable, self-regulating or responsive to stimuli, which may
or may not be physiological. Telemetry, physical connection or
remote signaling may be used to elicit a desired response.
[0253] In accordance with another aspect of the present invention,
the attenuation device accepts, captures, and/or translates
physical forces within the urinary tract to energize a site within
the attenuation device for the positive displacement of substances
outside the boundary of the attenuation device in either continuous
or bolus presentation.
[0254] In accordance with another aspect of the present invention,
there is provided a port/valve that is not associated with the
sealing edge of the attenuation device.
[0255] In accordance with another aspect of the present invention,
there is provided an attenuation device that includes a thin,
pliable safety tether 332 long enough to extend from the
attenuation device and exit from the meatus. See FIG. 24. The
tether can be constructed of accepted materials such as those used
in the manufacture of sutures, catheters and may also possess
anti-microbial properties. In one embodiment, the distal end of the
tether may be terminated with a lightweight pendant 334 of
sufficient bulk to prevent ingress of the entire tether into the
urethra. During normal use, the pendant may be temporarily affixed
to the patient's pelvic region. The tether may be used to remove or
deconstruct the attenuation device, and the tether provides the
patient with the capability of instant removal of the attenuation
device in the event the patient feels compelled to extract the
attenuation device.
[0256] In accordance with another aspect of the present invention,
there is provided an attenuation device that is a chambered
structure consisting of multiple subchambers for multiple
functions. See FIGS. 25 and 25A-C. The primary attenuation device
336 may or may not be fluidically connected to the secondary device
338. The fluidic connection 340 also acts as a tether with
sufficient service loop to allow the secondary device 338 to be
placed into the urethra while the primary attenuation device 336
remains untethered in the bladder 63, located above the pubic bone
69. During a urinary pressure spike, gas within the primary
attenuation device 336 compresses proportionally with the external
load. The compressed gas is then allowed to transfer to the
secondary device 338, dwelling in the urethra, and causing a
proportional expansion of the secondary device 338. The design of
the secondary device 338 directs expansion in an outward radial
direction, transverse to the longitudinal axis of the urethra, thus
augmenting the natural inward radial contraction of the urethra.
This type of "on demand" synchronous resistance augmentation may be
much more effective than other forms of passive or patient
controlled augmentation systems. Another benefit of this embodiment
of the present invention is that the synchronous outward radial
forces may help to positionally stabilize the secondary device
within the urethra. Passive devices must maintain a constant
retention capability (force or displacement of tissue) sufficient
to resist the maximum expulsion forces at all times. This level of
retention may lead to patient discomfort and cause long-term tissue
damage.
[0257] With reference to FIG. 25B, compression force (F.sub.comp)
342 equals the sum of ingress force (F.sub.ingress) 344 and the
egress force (F.sub.egress) 346. With reference to FIG. 25C, the
intravesical pressure 348 exhibits a rapid rise time and a rapid
decay time. The secondary device pressure 350 exhibits a rapid rise
time and a delayed decay time. FIG. 26 illustrates the effect of an
attenuation device on the intravesical pressure. Here, the
intravesical pressure 352 with the attenuation device exhibits
delayed rise and decay times and remains below the leakage pressure
of 80 cm H.sub.2O. This is contrast to the intravesical pressure
354 which exceeds the leakage pressure.
[0258] With reference to FIG. 27, in one embodiment, the
attenuation device 66 is anchored to the bladder wall 356. In
another embodiment, shown in FIG. 28, the attenuation device 66 is
part of a transurethrally-placed dynamic compliancy measurement
catheter 358. In other embodiments of the present invention, the
attenuation device may resemble a small three-spoked automotive
steering wheel, or a rotating toroidal space station. See FIG. 16A.
The outer ring would contain the attenuation device; the inwardly
radiating spokes would provide fluid conduits and mechanical
support for the secondary device attachment. The attenuation device
may also incorporate one or more shape holding super elastic wire
members to aid in positional stability. The secondary device could
resemble the distal tip section of a small diameter angioplasty
device and be affixed to the central hub.
[0259] In accordance with another aspect of the present invention,
a secondary device inflation/deflation response can be design
regulated. For example, it may be beneficial to inflate the
secondary as quickly as possible, but induce a response lag in the
deflation/inflation cycle to protect against a second cough, sneeze
or sudden mechanical shock.
[0260] In accordance with another aspect of the present invention,
there is provided a pressure compensator or bladder trainer that
can be implanted within a treatment site, such as, for example, the
abdominal cavity, and be hydraulically or pneumatically connected
to the bladder or be installed as a component of the bladder wall.
The device would be constructed of a rigid external enclosure to
shield the compressible elements from abdominal forces. The
function of this embodiment would be not only to manage the
transvascular pressure in treatment of a clinical insult, but also
to introduce pressure waves either outside or inside the bladder in
order to increase the muscle tone, compliance or affect the
neuromuscular elements of the bladder.
[0261] The embodiments of the present invention have been described
for use in the human anatomy. As understood by those skilled in the
art, the present invention is not limited to human use; rather
appropriately scaled versions of the inventions disclosed herein
can be used to provide clinical benefits to other animals,
including but not limited to mammalian household pets.
[0262] Certain embodiments of the present invention provide
significant advantages over prior art devices. These advantages
include but are not limited to: significant reductions in bladder
dysfunction related events; the ability to retrain a bladder with
other than normal compliance; no patient interaction required to
operate or maintain the attenuation device; patient is allowed to
void in a normal fashion; no infection conduit between the bladder
and the distal end of the meatus; minimal sensation generated by
the attenuation device; low cost to manufacture; cost effective
solution for patient when compared to existing treatments; and ease
of installation and removal for clinician.
[0263] In accordance with one aspect of the present invention,
there are provided devices and methods for measuring the dynamic
compliance of the bladder. In one embodiment, a device can be used
in combination with the fill tube/introducer to measure the dynamic
compliance of the bladder. One lumen of the fill tube can be used
to rapidly inflate the device, while pressure measurements of the
bladder are made via a second lumen. In one embodiment, the volume
is expanded by at least about 30 cc or 50 cc up to as much as 200
cc in a time period of from about 0.5 to 10 seconds to measure the
dynamic compliance of the bladder.
[0264] In accordance with another aspect of the present invention,
there are provided methods and devices for the restoration of
dynamic compliance of the bladder by retraining the bladder tissue
by introducing pressure waves at a prescribed place and with
prescribed characteristics.
[0265] In accordance with another aspect of the present invention,
there are provided methods and devices for the programmatic
delivery of clinical therapeutics in association with defined
pressure events. The present invention could be added to other
intravesical devices, such as Foley catheters, intravesical
infusers, such as those described in WO1998US0021368, filed Oct. 9,
1998, titled intravesical infuser (the disclosure of which is
incorporated in its entirety herein by reference), or the ends of
urethral stents to facilitate delivery, to treat multiple symptoms,
or to enhance the performance of either device. For example, the
attenuation device could work in combination with intravesical
infusers, to time the release of medications relative to pressure
events within the bladder.
[0266] In accordance with another aspect of the present invention,
there is provided an atraumatic method of measuring intravesical
pressure without the need for any external connection by placing a
pressure transducer and telemetry device within the attenuation
device. This secures the transducer within the bladder and prevents
the need to attach the transducer to the bladder wall.
[0267] FIG. 29 shows another attenuation device that can be placed
in pressure communication with a blood vessel. In particular, an
attenuation device 66 is shown implanted in a vessel 360 to
modulate or regulate blood pressure. The vessel 360 can be any
vessel in which pressure waves propagate and in which pressure
waves can be attenuated to provide a physiologic benefit. In some
applications, the vessel 360 is a vessel between the iliac arteries
and the heart. In some applications, the vessel 360 is a carotid
artery or other vessel carrying blood to the patient's brain. In
some applications, the vessel 360 is a vessel carrying blood from
the patient's brain. In some applications, the vessel 360 is the
patient's aorta. For example, the attenuation device 66 can
regulate pressure waves to protect a portion of the cardiovascular
system from being damaged due to exposure to normal or extreme
physiological events as discussed above. The attenuation device 66
can be used to reduce at least one of mean arterial pressure,
systolic pressure, diastolic pressure, and pulse pressure. The
attenuation device 66 can be used to protect the vasculature from
being damaged, e.g., from aneurysm or stroke, due to exposure to
normal or extreme pulsatile forces or normal or extreme
physiological events. An attenuation device can be placed in the
wall of the heart or within a major artery.
[0268] FIGS. 29A and 29B show the attenuation device 66 in a first,
enlarged or equilibrium state. The first state can correspond to
diastole or to diastolic pressure within the vasculature at the
location of the device. FIG. 29A depicts the attenuation device 66
in a second, reduced volume state. The second state is induced as a
response to a physiologic pressure spike. For example, the second
state could be due to an abnormal pressure spike, such as those
described herein, or a normal pressure increase due to systole.
[0269] FIGS. 29C and 29D illustrate that in some embodiments, a
pressure regulator or attenuation device 66' can be placed in
pressure communication with a blood vessel 360 without being in
fluid communication with the blood flowing therein. The pressure
regulator 66' is an elongated, tubular device in one embodiment
that is disposed at least partially around the exterior of a
segment of the vessel 360. The pressure regulator 66' can fully
encircle the vessel A in some embodiments. FIG. 29C illustrates
that in response to a physiologic pressure spike, the pressure
regulator 66' can be moved to a compressed state. In particular, an
internal volume and any fluid contained therein can be compressed
in response to the pressure spike. FIG. 29D illustrate that when
the physiologic pressure spike is not present, the pressure
regulator 66' moves to an expanded or relaxed state. The compressed
state of the pressure regulator 66' illustrated in FIG. 29C
effectively creates more volume within the vasculature compared to
the expanded state of the pressure regulator 66' illustrated in
FIG. 29D. FIG. 29D illustrates a relatively low pressure condition,
such as one corresponding to diastole.
[0270] FIGS. 29E-29G show an implantable pressure regulator 500
that can be used to manage blood pressure spikes in a patient's
vasculature. The pressure regulator 500 can be implanted outside
the vasculature as well. The pressure regulator 500 can be
configured as an elongate body, including a connection zone 504
disposed at least at one end thereof. Proximal and distal
connection zones 504 can be disposed at each end, as shown in FIGS.
29E-G. The pressure regulator 500 can include at least one
attenuation zone 508 to attenuate pressure spikes within a body
lumen, such as a blood vessel. In the embodiment of FIGS. 29E-G,
the pressure regulator 500 includes one attenuation zone 508 that
is substantially tubular in nature, though other shapes are
possible. The attenuation zone 508 can be located between a
plurality of connection zones 504 where more than one connection
zone is provided.
[0271] Any suitable material can be used to form part or all of the
pressure regulator 500, e.g., ePTFE, polyethylene, silicone, PEEK,
and other similar suitable polymeric materials. Preferably the
pressure regulator 500, e.g., within the attenuation zone 508, is
configured to be expandable in the range of pressures that can be
generated in the patient. Such a configuration can be achieved by
selecting a suitable material that is expandable under these
pressures at a wall thickness that is suitable for vascular
applications.
[0272] The attenuation zone 508 can be configured to expand to
provide a greater cross-sectional area therein at a time when a
relatively large pressure exists within the body portion, e.g.,
within a vessel. The amount of increase in cross-section area
should be at least enough to attenuate pressure during a pressure
spike to reduce the likelihood of or prevent a deleterious
condition in the blood vessel or other body structure near to or
remote from the pressure regulator 500. The attenuation zone 508
can be configured to provide a cross-sectional area that is at
least about 5% larger during a relatively high pressure (such as
one above an activation pressure) than the cross-section of the
resting attenuation zone 508 at STP. In another embodiment, the
attenuation zone 508 can be configured to provide a cross-section
that is at least about 10% larger during a relatively high pressure
(such as one above an activation pressure) than the cross-section
of the attenuation zone 508 at the resting pressure. In another
embodiment, the attenuation zone 508 can be configured to provide a
cross-section that is at least about 20% larger during a relatively
high pressure (such as one above an activation pressure) than the
cross-section of the unexpanded attenuation zone 508.
[0273] The attenuation zone 508 can be configured to expand from a
first, resting volume to a second, expanded volume to provide a
greater volume for carrying blood across its length at a time when
a relatively large pressure exists within the body portion, e.g.,
within a vessel. The amount of increase in blood carrying capacity
should be at least enough to attenuate pressure during a pressure
spike to reduce the likelihood of or prevent a deleterious
condition in the blood vessel or other body structure. The
attenuation zone 508 can be configured to provide at least about
105% of the resting state blood carrying volume during a relatively
high pressure (such as one above an activation pressure). In
another embodiment, the attenuation zone 508 can be configured to
provide at least about 110% of the resting state blood carrying
volume during a relatively high pressure (such as one above an
activation pressure). In another embodiment, the attenuation zone
508 can be configured to provide at least about 120% of the resting
state blood carrying volume during a relatively high pressure
spike.
[0274] In the embodiment of FIGS. 29E-29G, a first connection zone
504 is provided on a first end 512 of the pressure regulator 500
and a second connection zone 504 is provided on a second end 516 of
the pressure regulator. The attenuation zone 508 can be
substantially tubular, e.g., having a substantially circular
cross-section along at least a portion thereof. At least the
attenuation zone 508 of the pressure regulator 500 can include a
compliant material that enables the attenuation zone to move
between first and second states, as discussed above. Movement from
a first state corresponding to a pressure below a predetermined
threshold, which is illustrated in FIG. 29E, to a second state
corresponding to a pressure above the threshold, which is
illustrated in FIG. 29F, can be provided by expansion of the
pressure attenuator 500 within the attenuation zone 508. The first
state of FIG. 29E can correspond to the end of diastole, just prior
to systole and the second state of FIG. 29F can correspond to
systole, for example.
[0275] At least the attenuation zone 508 of the pressure regulator
500 can comprise a compliant material such as silicone, latex or
other elastomer, or composite structure that exhibits elastic
properties. The compliant material can be one that responds to a
reduction in pressure after a pressure spike by moving from an
expanded state, such as the second state, as illustrated in FIG.
29F, to an un-expanded state, as illustrated in FIG. 29E.
[0276] FIGS. 29H-J illustrate a pressure regulator 500' that is
similar to the regulator 500 except as described differently herein
below. The regulator 500' can be a tubular attenuation device that
includes a compliant attenuation zone. The regulator 500' includes
at least one connection zone 504'. For an in line configuration, a
connection zone 504' is provided on each end of the regulator 500'.
The connection zone 504' can be configured with an engagement
feature 520' that can be brought into engagement with portions of a
body conduit, e.g., a blood vessel to secure the regulator 500' to
the vessel. The engagement feature 520' is an expandable structure
in one arrangement. For example, the engagement feature 520' can be
a self expandable or balloon expandable stent or similar support
frame that can be expanded to bring the connection zone(s) into
engagement with an inner surface of a blood vessel. In one
arrangement, the engagement feature 520' is disposed on an inside
surface of a compliant tubular member that extends between first
and second ends 512', 516' of the pressure regulator 500'. The
engagement feature 520' can be an expandable and collapsible means
in some embodiments such that the pressure regulator 500' can be
applied and removed from the patient as needed. The response of the
device 500' to pressure variations within a blood vessel is similar
to that described above in connection with the regulator 500.
[0277] FIG. 29K illustrate that the pressure regulators described
herein, e.g., the pressure regulator 500 can be spliced into a
blood vessel. It can be spliced in using any method including but
not limited to suturing. For example, sutures can be threaded
through the connection zone(s) 504 at one or both ends of the
regulator 500 and through portions of a blood vessel A into which
the regulator is inserted, in accordance with vascular anastomosis
techniques that are understood in the art.
[0278] FIG. 29L depicts the pressure regulator 500' deployed in a
vessel A. The pressure regulator 500' includes an
expandable/collapsible means, such as that depicted in FIGS. 29H-J,
for mounting in the vessel A. The connection zone(s) 504' can be
expanded into engagement with an interior wall of the vessel A.
This technique is beneficial in that a vascular segment need not be
removed, as would be likely in a splice. This technique can be used
where the portion of the vessel A remains relatively compliant and
thus the attenuation zone 508' can expand to regulate physiologic
pressure spikes.
[0279] FIG. 29M shows the pressure regulator 500' with upstream and
downstream anastomotic connections for replacing a portion of a
blood vessel A that has been removed. The blood vessel portion can
be severed and/or removed using any suitable technique. Thereafter,
the first end 512' can be inserted into an upstream portion of the
vasculature and the second end 516' can be inserted into a
downstream portion of the vasculature. After the first and second
ends 512', 516' have been inserted, the engagement features 520'
can be expanded to bring the ends of the pressure regulator into
engagement with an inside surface of upstream and downstream
portions of the vasculature. The anastomosis may be augmented with
structures, adhesives or other techniques as desired. In the
illustration, the attenuation zone 508' is shown in an expanded
state, which can be induced by increased pressure, as discussed
above.
[0280] FIG. 29N is a schematic cross-sectional view through a
vessel, illustrating the pressure regulator 500' deployed within an
abdominal aortic aneurysm AAA. The enlarged aneurysmal sac of the
vessel provides a space into which the attenuation zone 508' can
expand to attenuate pressure. The pressure regulator 500' can be
deployed in other types of aneurysms as well and other vascular
structures where sufficient space or vascular compliance is present
to allow the attenuation zone 508' to expand and contract.
[0281] An attenuation device or pressure regulator, such as those
described herein, can be placed within the heart, such as in or on
a wall of the heart, within a major artery, or within the left
atrial appendage of the heart (see FIGS. 30A and 30B). Such
placement can facilitate reduction in risk of a cardiovascular
malady including, but not limited to renal failure, stroke, heart
attack, blindness. With reference to FIG. 30A, in one embodiment,
an air cell attenuation device 66 is positioned in the left atrial
appendage of the heart. With reference to FIG. 30B, in one
embodiment, a bellows-type attenuation device 66 is positioned in
the left atrial appendage.
[0282] An attenuation device can be placed on or within the right
side of the heart or in a pulmonary artery to reduce symptoms of
primary permanent hypertension. An attenuation device can also be
placed on the venous side of the vasculature system, such as within
the wall of the vena cava or attached to a Greenfield filter within
the vena cava to prevent portal hypertension and/or esophageal
varices. An attenuation device, such as an air cell, can be
attached to or encompass a stent for placement within the
vasculature.
[0283] In another embodiment, the attenuation device can be used in
the gall bladder to modulate pressure contained therein. Pressure
in the gall bladder may lead to undesired events such as the
formation of stones or pain for the patient. An attenuation device
can also be placed in the esophagus on the end of an NG tube to
limit spasm. With reference to FIG. 31, an attenuation device 66
can be placed in the bowel 364 to treat irritable bowel syndrome,
minimize Crohn's disease, cramping, or any other disorder resulting
from peristalsis.
[0284] In another embodiment, the attenuation device is used in the
field of ophthalmology to support cranio-facial tissue during
healing after a traumatic event or intraoptically as therapy for
acute angle closure glaucoma. In yet another embodiment, the
attenuation device is used in the field of orthopedics as an
implantable or external system to protect against pressure waves
and control the location of a healing bone after a traumatic event.
In still another embodiment, the attenuation device is used in the
field of otorhinolaryngology for the management of pressure waves
in the sinus cavities, including in and around the ears, the nose
and the throat. In another embodiment, an attenuation device is
placed in the lung to treat disorders such as, for example, asthma,
bronchial spasms or prevent damage from coughing in fragile lung
tissues in emphysema sufferers, etc. In yet still another
embodiment, an attenuation device is used to prevent Central
Nervous System ("CNS") problems such as, for example, head trauma,
cerebral edema, hydrocephalus, etc. Here, the attenuation device
can be placed in the epidural pocket under the skull.
[0285] In accordance with one aspect of the present invention,
there are provided air cell-like attenuation devices that are
placed in the bladder and/or other organs of the body and filled
with or comprise one or more compressible substances to provide
pressure compensation. Additionally, active, programmable pressure
compensators or generators are envisioned to monitor pressure
events, respond in a predetermined fashion and record or transmit
that information outside the body. Additionally, a reliable,
maintenance-free therapeutic delivery system is described to
programmatically release or distribute an agent into an organ of
the body using an erodible or deformable support matrix or material
of construction, and/or a programmable or responsive valving
system.
[0286] In accordance with one aspect of the present invention,
there is provided a compressible attenuation device having a valve
that permits filling of the attenuation device through a filling
device and yet resists deflation and/or additional filling of the
attenuation device after the filling device is removed. In one
embodiment, illustrated in FIGS. 36 and 37, the valve 80 is formed
by two parallel welds 281, 283 at the interface between two
complimentary surfaces--namely, the outer cover 280 and the
underlying layer 284. The valve 80 is in effect a collapsible
airflow passageway that remains in the collapsed position when the
filling device is removed, thereby preventing deflation when the
pressure within the attenuation device 66 is greater than the
pressure immediately outside the attenuation device and preventing
the additional filling of the attenuation device 66 when external
pressure is greater than the pressure within the attenuation device
66. The outer cover 280 and the underlying layer 284 function as
two flat sheets that stick together regardless of the relationship
between the internal attenuation device pressure and the immediate
external pressure. In one embodiment (not shown), one or more
adhesive materials or general locking mechanisms known in the art
of medical device design can be used to shut the value 80 upon
removal of the filling device. It should be noted that once the
filling device enters the valve at the entry point 82, the
attenuation device can be released and/or filled at any point
inside of the entry point 82, including but not limited to the
interface 282 between the valve 80 and the inside of the
attenuation device 66. The valve of the present embodiment can be
constructed according to the disclosure provided by U.S. Pat. No.
5,144,708, titled check valve for fluid bladders, issued Sep. 8,
1992, the disclosure of which is incorporated in its entirety
herein by reference.
[0287] In another embodiment, illustrated in FIG. 38, the valve 80
includes two duckbill structures that face opposite each other,
thereby permitting filling of the attenuation device through a
filling device while resisting deflation and/or additional filling
of the attenuation device after the filling device is removed. The
valve 80 generally comprises a tubular wall 81, having an aperture
82 in communication with a flow path 298. The valve has two sets of
first and second duck bill valve leaflets 86, 88, 290, 292 that are
attached to the tubular wall 81. Upon removal of the inflation
media source, the inflation media within attenuation device 66 in
combination with natural bias of the leaflets 86 and 88 cause the
leaflets to coapt, thereby preventing effluent flow of inflation
media through the flow path 83. In addition, the natural bias of
the leaflets 290 and 292 cause the leaflets to coapt, thereby
preventing the additional influx of media. It should be noted that
the internal section 294 of the tube will have a pressure equal to
the internal pressure of the attenuation device, whereas the
external portion or flow path 298 will have a pressure equal to the
immediate external pressure. A middle or neutral section 296 of the
tube is defined by the tubular wall and the two oppositely facing
duckbill structures defined by leaflets 86, 88, 290, 292.
[0288] In accordance with another aspect of the present invention,
there is provided an implantable self-inflating pressure
attenuation device that can inflate from a first, deflated
configuration to a second, at least partially inflated
configuration. Various transformable mediums can be used to inflate
the housing of the attenuation device from a deflated configuration
to at least a partially inflated configuration.
[0289] With reference to FIGS. 47A-47C, in one embodiment, the
transformable medium comprises a first reactant 432 and a second
reactant 434. Here, the implantable self-inflating pressure
attenuation device 430 (shown in its first, deflated configuration)
generally comprises a first reactant 432 and a second reactant 434,
which are physically separated from each other. When the first
reactant 432 comes into contact the second reactant 434, a chemical
reaction occurs within the attenuation device 430, thereby causing
the device attenuation 430 to transform into at least a partially
inflated configuration (not illustrated).
[0290] With reference to FIG. 47A, in one embodiment, the first
reactant 432 is contained within a balloon or container 436 that is
entirely contained within and free to move within the attenuation
device 430. The container 436 is generally impermeable to reactants
432, 434, and can comprise any suitable material known to those
skilled in the art. The suitability of a material for the container
436 will depend on the chemical characteristics of the reactants
432, 434. In another embodiment, illustrated in FIG. 47B, the
reactants 432, 434 are compartmentalized and separated within the
attenuation device 430 by a wall 438. The wall 438 is generally
impermeable to reactants 432, 434, and can comprise any suitable
material known to those skilled in the art. The suitability of a
material for the wall 438 will depend on the chemical
characteristics of the reactants 432, 434. In yet another
embodiment, shown in FIG. 47C, the attenuation device 430 has a
crease 440. The crease 440 separates the reactants 432, 434, and
thereby prevents the inflation/expansion reaction from occurring
until such inflation/expansion is desired and triggered by the
user. In still another embodiment (not illustrated), the reactants
432, 434 are separated within the attenuation device 430 by a
peelable bond, fold, and/or the like, known to those skilled in the
art.
[0291] In one embodiment, the medium capable of transformation
comprises gas generating compositions. Various compositions can be
used to generate gas in accordance with this invention. One class
of compositions is the combination of a base and an acid to produce
carbon dioxide. The acid and base are combined in dry form and
rendered reactive only when co-dissolved in water. Examples of
suitable bases are water-soluble carbonate and bicarbonate salts,
non-limiting examples of which are sodium bicarbonate, heat treated
sodium bicarbonate, sodium carbonate, magnesium carbonate,
potassium carbonate, and ammonium carbonate. Non-limiting examples
of suitable acids are citric acid, tartaric acid, acetic acid, and
fumaric acid. One presently preferred composition is a dry mixture
of sodium bicarbonate and citric acid. Compositions containing more
than one acid component or base component can also be used.
[0292] Gas generation can be initiated various ways, such as, for
example, contact with a fluid, temperature change, ignition, pH
change, etc. In one embodiment, the amount of gas generated is
equal to the amount of volume dissipated through the air cell,
thereby allowing for constant volume device until the gas
generating materials are exhausted.
[0293] The amount and rate of gas production can be controlled by
certain factors, such as, for example, the amount of reactive
materials or reactants, the amount of gas entrapped in the
structure, or the solubility of one or both of the chemicals in
water, etc. In one embodiment comprising a wick and tablet systems,
the available water as delivered by the wick to the tablet
dissolves only a limited amount of the reactants and resulting
reaction product(s). The reaction is thus limited by the solubility
of the chemicals in the limited amount of available water. The rate
of water delivery thereby controls the reaction rate. Some examples
of the solubility of suitable reaction chemicals per 100 grams of
water are as follows: sodium bicarbonate, about 10 g; citric acid,
about 200 g; tartaric acid, about 20 g; and fumaric acid, about 0.7
g. The limited solubility and limited water delivery rate through
the wick make it unnecessary to keep the acid and base separated
either before or during use of the infusion device.
[0294] It is further understood that a catalyst, another chemical
species or one of the byproducts of the reaction can propagate the
reaction and increase its speed. In the case of sodium bicarbonate
and citric acid, the byproducts are carbon dioxide, sodium citrate,
and water. A very small amount of water, such as, for example, 0.1
to 0.5 ml, can be used to start the reaction by dissolving the
sodium carbonate and citric acid. Since water is produced in the
reaction, the reaction speed increases until all of the reactants
are exhausted.
[0295] As a manufacturing aid, it may be desirable to add inert
agent(s) to the reactant composition to aid in the tableting
process and to keep the tablet intact during and after use.
Examples of suitable tableting aids include but are not limited to
polyvinyl pyrrolidone and anhydrous dibasic calcium phosphate, sold
by Edward Mendell Co. (Paterson, N.J., USA) as EMCOMPRESS.RTM..
Tableting aids can be eliminated for certain compositions with no
loss of performance. One such composition is the mixture of sodium
bicarbonate and citric acid.
[0296] Chemical compositions that produce oxygen or other gases can
also be used. A composition to generate oxygen in the presence of
water is disclosed in U.S. Pat. No. 4,405,486, titled Method for
Preparing granulated perborate salts containing a polymeric
fluorocarbon, issued Sep. 20, 1983, the disclosure of which is
incorporated in its entirety herein by reference. The controlled
rate of wicking water into such a tablet, and the limited
solubility of the constituents can control the rate of oxygen
release in a manner similar to that of carbon dioxide in the
systems described above.
[0297] In another embodiment, the medium capable of transformation
comprises peroxide and/or superoxide chemical systems. In certain
embodiments, gas is generated by drawing an aqueous solution of a
peroxide or superoxide into an absorbent tablet that contains an
enzyme or catalyst which promotes the decomposition of the peroxide
or superoxide to decomposition products including oxygen gas. In
another embodiment, a solid peroxide or superoxide can be
incorporated into the tablet, with oxygen generation being
initiated by contact of the peroxide or superoxide with water.
Hydrogen peroxide, for example, decomposes into water and oxygen,
providing no hazardous reaction products after infusion of the
liquid has been completed. Metal peroxides, such as, for example,
lithium peroxide, sodium peroxide, magnesium peroxide, calcium
peroxide, and zinc peroxide, etc., react with water to produce the
metal hydroxide and hydrogen peroxide, which then decomposes into
water and oxygen. Superoxides, such as, for example, sodium
superoxide, potassium superoxide, rubidium superoxide, cesium
superoxide, calcium superoxide, tetramethylammonium superoxide,
etc., react with water to produce the metal hydroxide and oxygen
gas directly. It will be noted that the production of hydrogen
peroxide itself is particularly preferred.
[0298] In one embodiment, a suitable tablet contains a water
absorbent material to facilitate the wicking action, and the enzyme
or catalyst in systems where enzymes or catalysts are used.
Examples of water absorbents useful for this purpose include
superabsorbent polymers, reconstituted cellulosic materials,
compressed zeolite powder (Types 13X and 4A, both unactivated),
etc.
[0299] One example of a suitable enzyme is catalase. Lyophilized
catalases are generally preferred. Catalysts effective for the
decomposition include metals deposited on high surface area
substrates, such as, for example, alumina, activated carbon, etc.
Examples of suitable catalysts include platinum, palladium, silver,
etc.
[0300] Chemical reactants can also be used rather than enzymes or
catalysts to decompose hydrogen peroxide. Examples of such
reactants include but are not limited to potassium permanganate,
sodium hydroxide, etc. It should be noted, however, that there are
safety concerns associated with potassium permanganate and sodium
hydroxide.
[0301] As between enzymes and catalysts, enzymes provide a cost
benefit for single-use systems. For reusable systems, however,
catalysts are generally preferred. One significant advantage to the
use of a hydrogen peroxide system with a catalyst is the ability to
regenerate the system by drying out the tablet and adding more
hydrogen peroxide solution to the water reservoir. Regeneration in
this type of system is thus easier than regeneration of an
absorbent tablet for a system that requires adsorbed gas.
[0302] In another embodiment, the medium capable of transformation
comprises chemical reactants that are used effectively to generate
a gas to push a fluid from an infusion pump. In order to generate
carbon dioxide, two or more reactive chemicals are mixed that, upon
reaction, generate a gas. Preferably, one of the reactants is
provided in liquid form, i.e., a liquid chemical, a solution, or
the like, and another one of the reactants is provided as a solid.
Either the liquid or the solid may comprise more than one reactive
chemical. However, in one preferred embodiment, each of the liquid
and the solid contain only one reactive species.
[0303] Carbon dioxide is generally quite inert and safe at low
concentrations. However, other gases could also be used, provided
they are relatively inert and safe. For the purposes of the
following discussion, it will be assumed that carbon dioxide is to
be generated. As mentioned above, to generate the gas, at least two
reactants are caused to come into contact. For ease of reference,
the reactants will be referred to herein as a first reactant and a
second reactant or a solid reactant and a liquid reactant, and
particular sets of reactants will be referred to as reactant
sets.
[0304] First Reactant: Preferably, the first reactant is selected
from a group consisting of carbonates and bicarbonates,
particularly, Group I and II metal carbonates and bicarbonates (the
"carbonate"). For example, in one embodiment, preferred carbonates
include sodium bicarbonate, sodium carbonate, magnesium carbonate,
and calcium carbonate. However, sodium bicarbonate, sodium
carbonate and calcium carbonate are highly preferred, with sodium
carbonate (or soda ash) being the most highly preferred. One
desirable feature of sodium carbonate is that it is easily
sterilizable. For example, sodium carbonate can be sterilized with
heat, such as through autoclaving. This is preferable, since the
infusion devices for use with the invention are designed for human
use and it is safer to ensure that all of the components are
sterile whether it is expected that they will come into contact
with the patient or not. Other reactants that are sterilizable with
heat, ethylene exposure, or exposure to ionizing radiation are
equally useful.
[0305] The carbonate can be either used as a solid reactant or can
be dissolved in a solution to form a liquid reactant. In one
preferred embodiment, the carbonate is used as a solid. The reason
for this choice is that the carbonates are all solids and some are
only sparingly soluble in water.
[0306] Second Reactant: The second reactant is preferably an acid.
Preferably, the acid is selected from the group consisting of
acids, acid anhydrides, and acid salts. Preferably, the second
reactive chemical is citric acid, acetic acid, acetic anhydride, or
sodium bisulfate. Usually the second reactant is used as the liquid
reactant. However, in the case of citric acid and sodium bisulfate,
for example, the second reactant can also be the solid reactant.
Nevertheless, the second reactant is generally more soluble in
water than the first reactant and is, therefore, used to form the
liquid reactant.
[0307] Reactant Sets: A reactant set is based upon a variety of
considerations. For example, the solubility of the first and second
reactants is considered to determine which reactant should be used
as the solid or liquid reactant. Also considered is the product of
the reaction and its solubility. It is preferred that the products
be CO.sub.2 gas and a soluble inert compound. Once these factors
are considered, appropriate reactant sets can be constructed. For
instance, in one embodiment, reaction sets such as those shown in
Table I are preferred.
TABLE-US-00001 TABLE I Solid Reactant Liquid Reactant Sodium
Carbonate Citric Acid Calcium Carbonate Acetic Acid Magnesium
Carbonate Citric Acid
[0308] Additional details may be found in U.S. Pat. No. 5,992,700,
titled controlled gas generation for gas-driven infusion devices,
issued Nov. 30, 1999, and U.S. Pat. No. 5,588,556, titled method
for generating gas to deliver liquid from a container, issued Dec.
31, 1996. Both of these patents are hereby incorporated by
reference herein and made a part of this specification.
[0309] In another embodiment, the method of producing gas is
entrapped pressurized gas in a sugar or a porous molecular sieve.
Generally, gas is liberated when the structure comes in contact
with a fluid.
[0310] In accordance with another aspect of the present invention,
there is provided a method of delivering the implantable
self-inflating pressure attenuation device 430 into the treatment
site, such as, for example, the bladder. With reference to FIGS.
48A-48D, in one embodiment, the delivery system 450 includes a
bifurcated delivery tool 452 and a delivery cannula 454. The tool
452 has a fork-like shape and can be extended out and retracted
into the cannula 454. As illustrated, the bifurcations of the tool
452 are spaced so as to squeeze or pinch the device 430, thereby
separating a first portion 444 of the attenuation device 430 from a
second portion 446, and thereby separating a first reactant 432
from a second reactant 434. Because the reactants 432, 434 do not
come into contact with each other, the device remains in its
deflated state, thereby facilitating the procedure of delivering
the attenuation device 430 to the treatment site, such as, for
example, the bladder. In one embodiment, shown in FIGS. 48B and
48C, first and second portions 444, 446 of the deflated attenuation
device are wound about itself along the axis of the tool 452,
thereby minimizing the volume of the attenuation device 430, and
thereby facilitating the delivery of the attenuation device 430
into the treatment site.
[0311] In accordance with another aspect of the present invention,
there is provided a method of improving the dynamic compliance
and/or contractility of the bladder.
[0312] Histology: The mucosa of the bladder is composed of
transitional epithelium. Beneath it is a well-developed submucosal
layer formed largely of connective and elastic tissues. With
reference to FIGS. 40A and 40B, the connective and elastic tissues
of the bladder wall generally comprise mucosa 394, elastin 396,
collagen 398, and muscle 400.
[0313] With reference to FIG. 40A, as in most tissues, collagen 398
is arranged as a coiled or complex helical material within the
bladder wall. While collagen 398 itself is not very elastic
(distensible), the coiled configuration allows expansion of the
collagen bundle. When the bundle is extended (see FIG. 40B), the
uncoiled collagen length becomes the limiting size. It is at this
point that tension rises rapidly, analogous to the twisting of
several strands of rope. When twisted, the combined strands
shorten. The combined strands can be lengthened by untwisting
without stretching any individual strand. As in other tissues, as
the patient ages the elastin 396 converts to collagen 398, reducing
the compliance of the bladder 63. External to the submucosa is the
detrusor muscle 400, which is made up of a mixture of smooth muscle
fibers arranged in a random, longitudinal, circular, and spiral
manner.
[0314] Physiology: The functioning of the bladder includes
contributions from each of the layers of the bladder 63 described
above. One method of understanding the properties of the bladder
over time is to evaluate a cystometrogram, which, in one
embodiment, is generated by reasonably slow continuous filling of
the bladder 63. FIG. 41 illustrates a typical cystometrogram.
Initially, during Phase I 402 when the bladder 63 is empty, elastic
elements are not stretched. Here, the bladder is in a collapsed
state and none of the materials within the wall are expanded.
Accordingly, there will be no tension within the wall and pressure
within the bladder will be relatively low. During Phase II 404, as
fluid fills the bladder, the walls unfold and elastic structures
start to stretch. Now there is some tension and bladder pressure
rises. As the bladder continues to fill, and the elastic tension
continues to increase, the radius increases as well. From the Law
of Laplace for a sphere, (P=2T/R), it will be noted that in order
for pressure to remain constant, the proportion between tension and
radius must remain constant. During Phase III 406, as the bladder
capacity is reached, collagen and/or other less elastic materials
have become unfolded and are themselves subject to stress. Since
their modulus of elasticity is less than that for elastin and for
the other elements on stress up to this point, the wall tension
rises quickly and bladder fluid pressure rises steeply. A slight
increase in volume or radius will now produce a rapid change in
pressure. As this stretch occurs, neurological factors apply as
afferent impulses from the bladder in response to stretch begin to
occur with a significant frequency.
[0315] Therapeutic Benefits, Methods of Improving the Dynamic
Compliance of the Bladder, Methods of Improving the Contractility
of the Bladder: Based on demonstrations by Solace, Inc. it is
believed that the removal of high frequency, repetitious insults to
the bladder wall for a 5 day to 180 day period of time increases
the dynamic compliance of the bladder and reduces symptoms of
incontinence by: precluding/reducing the stretch of elastin fibers;
reducing of the conversion of elastin fibers into collagen;
allowing the "stretched" muscles of the bladder wall to shorten,
thereby improving compliance and bladder wall contractility;
removing pressures exerted on the pelvic floor and connective
tissues, allowing retraining and healing, increasing urethral
resistance; placing the attenuation device in the bladder provides
passive resistance to the bladder neck and bladder wall, allowing
the muscles to strengthen. These and other therapeutic benefits
could last up to about 30 days to about one year. One additional
benefit of attenuation and/or improving bladder compliance includes
improved flow during voiding (i.e. method of improving flow during
voiding by "smoothing" the pressure within the bladder). Abdominal
straining, resulting in a raised abdominal pressure P.sub.abd and,
therefore, an increased intravesical pressure is not often employed
in normal voiding, nor is it usually as efficient as detrusor
contraction in producing voiding. If, however, the detrusor
contraction is weak or absent abdominal straining may be the only
available way of voiding and may then become of primary
importance.
[0316] The detrusor pressure is not by itself a measure of the
strength of the detrusor contraction. A satisfactorily contracting
detrusor can produce either a high detrusor pressure and a low
flow-rate, or a low pressure and a high flow-rate. The tradeoff
between the pressure generated and the flow produced results from
the force/velocity relationship characteristic of any contracting
muscle. Consequently, for patients with low dynamic bladder
compliance, any pressure changes during flow can significantly
decrease flow rates. For patients that have weak detrusor
contractions and/or those that "bear down" for force urine out of
the bladder, sometimes referred to "Val Salva voiders," there is
great pressure fluctuations within the bladder during voiding,
resulting in reduced flow rates. By attenuating pressures within
these patients via an attenuation device, improved flow can be
achieved.
[0317] Another benefit of attenuation and/or improving bladder
compliance includes improved urethral closure pressures. Changes in
abdominal pressure affect not only the intravesical pressure but
also the urethra, proximally by direct mechanical action. The
result is that when the abdominal pressure rises, as during
straining or a cough, the urethral pressure discussed above also
rises. The maximum urethral closure pressure therefore does not
diminish, and may even increase. This represents a natural defense
against leakage during stress. This process is enhanced by the
attenuation of intravesical pressures within the bladder, with full
exposure of the urethra to increased abdominal pressures.
[0318] Another benefit of attenuation and/or improving bladder
compliance includes improving the symptoms of benign prostatic
hypertrophy ("BPH"). As the prostate enlarges, flow rates are
reduced and residual volumes increase. The symptoms of low flow are
increased as the increased intravesical pressure causes a decrease
in the compliance of the bladder wall, bladder muscles elongate,
elastin converts to collagen in the most severe cases), making it
even more difficult for the bladder to "push" the urine through the
restricted opening of the prostate. As this cascade continues, the
symptoms of benign prostate hyperplasia increase. Placement of an
attenuation device in the bladder reduces symptoms of BPH by
improving flow, increasing the compliance of the bladder wall,
removing high pressure insults to the bladder wall, and allowing
the bladder wall muscles to shorten, all permitting the bladder to
more effectively "push" the urine through the urethra and prostate.
In one embodiment, the attenuation device in the bladder reduces
the symptom of BPH by attenuating increases in pressure within the
bladder by reversibly reducing its volume in response to the
pressure increases. For example, in one embodiment, the attenuation
device reduces its volume by at least 5%. In another embodiment,
the attenuation device reduces its volume by at least 10%. In yet
another embodiment, the attenuation device reduces its volume by at
least 25%.
[0319] Conformable Device: Patients generally experience pain and
irritation when any foreign object is either wholly or partially in
the bladder or bladder neck. With reference to FIG. 42, this pain
can occur when the bladder or bladder neck has collapsed onto the
foreign object 408, perhaps within a fold of the bladder; the
pressure exerted on the bladder wall by focal points on the device
creates pain and irritation. This pain is typically more acute when
the patient is in the horizontal position.
[0320] With reference to FIG. 43, to eliminate pain and irritation
of the bladder and bladder neck when the bladder collapses on to
any device (wholly or partially in the bladder and bladder neck),
the shape of the attenuation device 410 can change to conform to
the bladder wall in order to maximize the surface area of the
attenuation device in contact with the bladder wall so as to
dissipate the pressure over as large a surface area of the bladder
wall as possible, and thereby prevent the focal points that cause
trauma, pain, or irritation to the bladder. In one embodiment, the
attenuation device has a compressible wall, thereby resulting in a
conformable device where the medium (e.g., gas) within the device
can move out of a fold in the bladder wall to reduce trauma.
Examples of such attenuation devices 410 include but are not
limited to: attenuation device having 15 cc of air in a container
that is capable of holding 30 cc of volume; Foley catheter or other
catheter having an inflatable anchoring balloon; drug delivery
infuser; J stent; etc.
[0321] FIGS. 39A-D illustrates attenuation (i.e. pressure
reduction) with various attenuation device air volumes. The data
for these graphs were generated using a bench top bladder
simulation program. Here, the maximum spike pressure is 2.0 psi.
The spike event duration is approximately 40 ms, which is
approximately equivalent to the duration of a coughing or sneezing
event. With reference to FIG. 39A, a test was conducted with a 250
mL rigid plastic container filled with synthetic urine. A regulated
pressure of 2.0 psi was introduced into the container via a
controlled solenoid valve. A pressure transducer detected the
pressure rise. Here, the pressure rise time (Tr) of the container
pressure 422 to reach 2.0 psi was approximately 40 ms. With
reference to FIG. 39B, a similar test was conducted on a 250 mL
rigid plastic container. Here, an attenuation device filled with 15
mL of air was placed inside the container willed with synthetic
urine. Here, the Tr of the container pressure 424 to reach 2.0 psi
was approximately 195 msec. Thus the attenuation device slowed the
rise time by 4.8.times.. During the spike event (i.e. when time
equaled 40 ms), the pressure inside the container reached 0.7 psi
(vs. 2 psi), resulting in a 65% reduction of pressure vs. baseline.
With reference to FIG. 39C, a similar test was conducted; the only
difference being that the attenuation device was filled with 25 mL
of air. Here, the Tr of the container pressure 426 to reach 2.0 psi
was approximately 290 ms. Thus the attenuation device slowed the
rise time by 7.25.times.. During the spike event (i.e. when time
equaled 40 ms), the pressure inside the container reached 0.5 psi
(vs. 2 psi), resulting in a 75% reduction of pressure vs. baseline.
With reference to FIG. 39D, a similar test was conducted; the only
difference being that the attenuation device was filled with 30 mL
of air. Here, the Tr of the container pressure 428 to reach 2.0 psi
was approximately 340 ms. Thus the attenuation device slowed the
rise time by 8.5.times.. During the spike event (i.e. when time
equaled 40 ms), the pressure inside the container reached 0.4 psi
(vs. 2 psi), resulting in an 80% reduction of pressure vs.
baseline.
[0322] FIGS. 44A-D show pressure vs. time curves generated by a
bench top bladder simulator. FIG. 44A shows the baseline
pressure-time curve without an attenuation device. FIG. 44B shows
the pressure-time curve with an attenuation device having a 15 cc
air volume. FIG. 44C shows the pressure-time curve with an
attenuation device having a 25 cc air volume. FIG. 44D shows the
pressure-time curve with an attenuation device having a 30 cc air
volume.
[0323] Algorithm(s) for Measuring Leak Point Pressures: Typical
measurement of a patients leak point pressure is taken with
pressure catheters in the bladder and in the rectum. The patient
tightens the abdominal and pelvic muscles (valsalva) to increase
the external pressure exerted on the bladder. At the time when the
test administrator identifies visually that leakage has occurred, a
button is pressed, and the most recent pressure data points are
recorded. Typical urodynamic equipment in use today measures 2 to
35 data points per second. Given the time delay from when leakage
occurs and when leakage is evident to the test administrator, and
the fact that pressure decreases when leakage occurs, one
embodiment of a more accurate method of measuring leak point
pressure involves measuring pressure at the rate of 1000 pts per
second, and programming or setting a computer to look at the prior
5/3/2/1 second(s) and to look for the peak-generated pressures when
the clinician presses the "leak" button (i.e. a button on or in
communication with the computer that the clinician pushes upon
seeing or detecting leakage).
[0324] In accordance with another aspect of the present invention,
there is provided a method of attenuating pressure changes in the
bladder by introducing one or more low permeability gases and/or
fluids with higher vapor pressures into an attenuation device. A
lower permeability and higher vapor pressure gas or fluid usually
has a higher density than air or water, respectively. The
solubility of the gas or fluid in urine is commonly very low. With
reference to FIG. 49, the illustrative embodiments described herein
show an attenuation device 66 with one high vapor pressure gas or
fluid. However, it will be understood that the attenuation device
66 can have one or more high vapor pressure media (i.e. gases
and/or fluids, or combinations thereof). Outside the body, the
atmospheric pressure (P.sub.a) is equal to the partial pressure of
air (P.sub.Air). The pressure within the bladder (P.sub.b) is
approximately equal to P.sub.a; however, in practice, P.sub.b is
slightly higher P.sub.a. For example, if P.sub.a is 14.7 psi or 1
atm, then P.sub.b can be approximately 14.85 psi (i.e. 14.7
psi+0.15 psi). There is a usually a pressure gradient from P.sub.b
to P.sub.a within the tissues 464 of the body moving from the walls
466 of an individual's bladder 468 to the surrounding atmosphere
460 outside the skin 462. Since P.sub.b is greater than P.sub.a,
the pressure gradient results in the transfer of gases from the
inside the body, such as, for example, from within the bladder
outward through the pores in the skin 462 of an individual. The
total pressure within the attenuation device (P.sub.T) (i.e. within
the outer wall 470 of the attenuation device 66) is equal to the
sum of partial or vapor pressures of the high vapor pressure gas or
fluid (P.sub.HD) and P.sub.Air.
[0325] With reference to FIG. 49, in one embodiment, the
attenuation device 66 comprises an outer wall 470 and a high vapor
pressure gas or fluid that generally has low permeability through
the outer wall 470. In one embodiment, the wall 470 comprises a
material, such as, for example, polyurethane, that is characterized
by low permeability for the high vapor pressure media and moderate
to high permeability for air. Examples of suitable high vapor
pressure media include, but are not limited to: sulfur hexafluoride
hexafluoroethane; perfluorocarbons ranging from perfluoropropane,
perfluorobutane, perfluoropentane, perfluorohexane,
perfluoroheptane, perfluorooctane, perfluorodecalin,
octafluoropropane, decafluoro-n-butane, perfluorooctylbromide to
perfluoroperhydrophenanthrene; and inhaler propellants like
heptafluoropropane and tetrafluoroethane.
[0326] With continued reference to FIG. 49, air is dissolved in the
urine in the bladder. As explained above, P.sub.b is slightly
greater than P.sub.Air. Here, P.sub.T=P.sub.b=P.sub.HD+P.sub.Air.
In one embodiment, if the material of the attenuation device 66
does not allow the higher vapor pressure gas to permeate through
the device 66, air is driven into the attenuation device until the
partial pressure of air in the urine matches the partial pressure
of air in the attenuation device. In another embodiment, if a high
vapor pressure fluid with a vapor pressure (P.sub.HD) greater than
the bladder pressure and a low permeability rate through the
attenuation device wall were put into the attenuation device 66,
air would be driven into the device 66 until the partial pressures
of air are equal in the attenuation device 66 and in the urine.
With a reservoir of fluid in the attenuation device 66 more vapor
could be evaporated when P.sub.b decreases and vapor would condense
when the P.sub.b increases, thereby resulting in a constant
pressure system.
[0327] In one embodiment, where the average P.sub.b is known, a
constant volume system is achieved by using a wall material that is
generally taut and rigid in structure, such as, for example,
silicone, polyurethane or any derivative thereof, that allows
permeability to air but not to the selected high vapor pressure gas
or fluid/vapor. Here, the attenuation device 66 is placed deflated
into the bladder. A mixture of air and higher vapor pressure gas or
fluid is injected into the attenuation device 66 so that the
P.sub.HD matches the average pressure of the bladder (P.sub.b)
minus the atmospheric pressure (P.sub.a). If there is no loss of
the higher vapor pressure gas or fluid/vapor through the
attenuation device wall, an equilibrium point is reached when the
partial pressure of air in the attenuation device matches the
partial pressure of air in urine. If the volume of gas in the
attenuation device 66 puts no tension on the wall of the
attenuation device, then the vapor or partial pressure of the
higher vapor pressure gas or vapor equals the average bladder
pressure minus the atmospheric pressure and the partial pressure of
air in the attenuation device equals the partial pressure of air in
the urine.
[0328] It will be noted that the pressure in the bladder typically
ranges from 0 to 2 psi and is a function of the lifestyle of the
individual. In one embodiment, comprising a constant pressure
system, the wall of the attenuation device 66 can be designed to
provide tension to control volume changes due to pressure
variations in the bladder. For example, in one embodiment, if the
attenuation device 66 were designed to match an average bladder
pressure of 0.15 psi but the individual's bladder pressure is
higher, air would be forced out of the attenuation device 66 until
the partial pressure of air balances between the attenuation device
and the urine or all of the air is forced out of the attenuation
device. If the bladder pressure were lower, air would be driven
into the attenuation device until the tension on the walls of the
attenuation device results in the internal partial pressure of air
equaling the bladder partial pressure of air.
[0329] FIGS. 50A and 50C illustrate a pressure regulator or
attenuation device 600 that includes a connection zone 604 for
connecting to a body conduit and an attenuation zone 608. The
connection zone 604 is configured to be placed in pressure
communication with or proximity to the cardiovascular system. For
example, the connection zone 604 can be sutured or otherwise
affixed to the cardiovascular system. The attenuation zone can
comprise a compliant material or a variable volume structure
configured to have compliant properties. The pressure regulator 600
can be coupled with the vessel A with or without creating an
opening or portal in the vessel.
[0330] FIG. 50A depicts the pressure regulator 600 in fluid
communication with a vessel through connection zone 604 and
corresponding opening the vessel wall during a relatively low
pressure phase, such as diastole. FIG. 50C depicts the pressure
regulator 600 during a relatively high pressure phase, e.g., during
systole or a random high pressure event.
[0331] FIGS. 50B and 50D illustrate another pressure regulator 620
that can be implanted within a patient. The pressure regulator 620
includes a connection zone 624 that can include connection portions
at first and second ends 628, 632. An attenuation zone 636 can be
disposed between the first and second ends 628, 632. The
attenuation zone 636 can be formed of a compliant material, such as
is discussed above. The connection zone 624 can be affixed to the
cardiovascular system at first and second locations 640, 644. The
pressure regulator 620 can be affixed with or without creating one
or more portals or openings into the vessel A.
[0332] FIG. 50B depicts the pressure regulator attenuation 620
during a relatively low pressure phase, such as diastole. FIG. 50D
depicts the pressure regulator attenuation 620 during a relatively
high pressure phase, e.g., during systole or a random high pressure
event.
[0333] In the embodiment illustrated in FIG. 50C, connection zone
604 is illustrated as attached via a side anastomosis to the parent
vessel and leading directly to the expandable reservoir or
attenuation zone 608. However, the attenuation zone 608 may be
positioned remotely from the connection to the parent vessel. For
example, the attenuation zone might be at least about 2 cm, in some
embodiments at least about 10 cm, and, if desired, at least about
20 cm from the parent vessel access point, depending upon the
access point and desired location of the attenuator. For example,
the access point may be located on the aorta, subclavian artery,
brachial artery, carotid artery, or other point in the vasculature.
The vascular access point may be in fluid communication with the
attenuator by an elongate flexible tubular body which extends
subcutaneously to a remote attenuator, which may be positioned in
the vicinity of the clavicle, in the abdomen, or elsewhere as may
be desired. The elongate flexible tubular body may be a pressure
line connecting the vascular access point to the attenuator. The
pressure line may be filled with any of a variety of media such as
a non-compressible liquid (e.g. saline) or a compressible gas such
as carbon dioxide or air.
[0334] Similarly, the embodiment of FIG. 50D may be connected into
the vasculature at a first point and a second point which are
remote from the location of the attenuator. The first and second
attachment points may be connected to the same parent vessel, as
illustrated in FIG. 50D. Alternatively, the pressure regulator 620
may be connected such that it functions as a shunt between a first
vessel and a second vessel. The first and second vessels might be
two positions on the same artery, to different arteries, or an
artery and a vein. A venous to venous shunt may also be
accomplished with the in-line attenuators of the present invention,
although purely venous side pressure attenuation may be less common
than on the arterial side of the cardiovascular system. Pressure
attenuating arterial vascular shunts may be utilized in any of a
variety of locations within the body, such as in the intracranial
vasculature, the coronary vasculature, and the peripheral
vasculature as will be apparent to those of skill in the art in
view of the disclosure herein.
[0335] FIGS. 51A-51B show another embodiment of a pressure
regulator 680. The pressure regulator 680 includes an attenuation
zone or device 684 that is placed partially within a body cavity or
blood vessel and partially outside the body cavity or vessel. The
regulator 680 can be applied partially within the body any
partially outside the body. A partially implanted device could be
used temporarily or permanently. In a temporary application it may
be beneficial to mount the attenuator on an elongated means such as
a catheter. A temporary system may be of benefit in a clinical
scenario such as hypertensive crisis when the systolic blood
pressure should be lowered quickly.
[0336] FIGS. 51A-51B show the pressure regulator partially in the
cardiovascular system and partially outside the cardiovascular
system. FIG. 51A shows that the pressure regulator 680 includes a
first portion 684 that can be enlarged and a second portion 688
that also can be enlarged. The first portion 684 can include a
cavity in which a fluid can reside. The second portion 688 also can
include a cavity in which a fluid can reside. In one embodiment, a
fluid flow path 672 is provided to convey a fluid between cavities
in the first and second portion 684, 688. The pressure regulator
680 preferably is configured such that at least some of the fluid
is urged into a first cavity in the first portion 684 when a
relatively low pressure exists in the cavity or vessel in which the
pressure regulator 680 is disposed. Such a condition is illustrated
in FIG. 51A and could correspond to diastole. The pressure
regulator 680 preferably also is configured such that at least some
of the fluid is urged into a second cavity in the second portion
688 when a relatively high pressure exists in the cavity or vessel
in which the pressure regulator 680 is disposed. Such a condition
is illustrated in FIG. 51B and could correspond to systole.
[0337] One technique for generally urging the fluid into a cavity
associated with the first portion 684 is to control the wall
thickness of the first and second portions 684, 688. In particular,
by providing a relatively thin wall in the first portion 684, the
first portion may expand under pressure of the fluid in the
pressure regulator 680. This would tend to urge fluid into the
first portion 684 absent a change in external conditions. In
another arrangement, the first portion 684 can include a more
compliant material than the second portion 688, which will tend to
urge fluid into the first portion when the regulator 680 is at
rest.
[0338] Preferably, a housing will be provided for surrounding the
second portion 688, to prevent compression of the second portion
688 as resulted of outside forces. As with previous embodiments,
the fluid flow path 672 may be as long as desired, to enable
positioning the second portion 688 at a location in or adjacent the
body independent of the vascular access point utilized for
positioning the first portion 684 within the vasculature.
[0339] Having thus described certain embodiments of the present
invention, various alterations, modifications and improvements will
be apparent to those of ordinary skill in the art. Such
alterations, variations and improvements are intended to be within
the spirit and scope of the present invention. Accordingly, the
foregoing description is by way of example and is not intended to
be limiting. In addition, we have described a variety of pressure
attenuators including but not limited to gas filled and mechanical.
However, other attenuating pressure attenuating devices may be
used, such as a device filled with a medium that phase changes at a
particular pressure. In addition, any dimensions that appear in the
foregoing description and/or the figures are intended to be
exemplary and should not be construed to be limiting on the scope
of the present invention described herein.
* * * * *