U.S. patent application number 16/568122 was filed with the patent office on 2020-01-16 for intravascular devices, systems, and methods having drive cables with a lubricious coating and/or radiopaque markers.
The applicant listed for this patent is KONINKLIJKE PHILIPS N.V.. Invention is credited to Chris LEBLANC, Jeremy STIGALL.
Application Number | 20200015778 16/568122 |
Document ID | / |
Family ID | 54554560 |
Filed Date | 2020-01-16 |
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United States Patent
Application |
20200015778 |
Kind Code |
A1 |
STIGALL; Jeremy ; et
al. |
January 16, 2020 |
INTRAVASCULAR DEVICES, SYSTEMS, AND METHODS HAVING DRIVE CABLES
WITH A LUBRICIOUS COATING AND/OR RADIOPAQUE MARKERS
Abstract
Rotational intravascular ultrasound (IVUS) imaging devices and
systems are provided. The IVUS imaging devices include catheters
having a rotating drive cable with a transducer disposed at a
distal end thereof for imaging a bodily vessel of interest. In some
embodiments, a lubricious coating is applied on the drive cable to
promote uniform rotation of the drive cable and the transducer. In
some embodiments, the drive cable is coated with a polymer layer to
promote uniform rotation of the drive cable and the transducer. In
some embodiments, radiopaque markers are affixed on the drive cable
for accurate placement of the transducer within of the vessel and
for accurate measurement of internal dimensions and lesion lengths
within the body of the patient.
Inventors: |
STIGALL; Jeremy; (CARLSBAD,
CA) ; LEBLANC; Chris; (CARLSBAD, CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
KONINKLIJKE PHILIPS N.V. |
EINDHOVEN |
|
NL |
|
|
Family ID: |
54554560 |
Appl. No.: |
16/568122 |
Filed: |
September 11, 2019 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
14716462 |
May 19, 2015 |
10413273 |
|
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16568122 |
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62000810 |
May 20, 2014 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61B 8/445 20130101;
A61M 25/0108 20130101; A61B 8/4245 20130101; A61B 8/4461 20130101;
A61B 8/12 20130101; A61B 8/0841 20130101; A61M 2210/12 20130101;
A61B 6/12 20130101 |
International
Class: |
A61B 8/12 20060101
A61B008/12; A61M 25/01 20060101 A61M025/01; A61B 8/00 20060101
A61B008/00 |
Claims
1. A rotational intravascular ultrasound (IVUS) device, comprising:
a drive cable configured to rotate about an axis of rotation
associated with the IVUS device; and a transducer coupled to a
distal end of the flexible drive cable such that the transducer
rotates with the drive cable; wherein the drive cable is coated
with a lubricious coating configured to enable uniform rotation of
the drive cable and the transducer by reducing frictional forces
experienced by the drive cable.
2. The rotational IVUS device of claim 1, wherein the lubricious
coating is a hydrophobic coating.
3. The rotational IVUS device of claim 1, wherein the lubricious
coating is a hydrophilic coating.
4. The rotational IVUS device of claim 1, further comprising a
sheath surrounding the drive cable, wherein the lubricious coating
is configured to reduce rotational friction between the drive cable
and the sheath.
5. The rotational IVUS device of claim 4, wherein the sheath is
configured to be filled with a fluid, wherein the lubricious
coating is configured to reduce rotational friction between the
drive cable and the fluid.
6. The rotational IVUS device of claim 1, wherein the lubricious
coating is in direct contact with the drive cable.
7. The rotational IVUS device of claim 1, wherein lubricious
coating is water-based.
8. The rotational IVUS device of claim 1, wherein lubricious
coating is solvent-based.
9. The rotational IVUS device of claim 1, further comprising a
polymer layer fixedly secured to and surrounding the drive cable
without enclosing the transducer.
10. The rotational IVUS device of claim 9, wherein the polymer
layer includes at least one of a high density polyimide layer, a
low density polyimide layer, or polyimide ethylene layer.
11. The rotational IVUS device of claim 9, wherein the polymer
layer is in direct contact with the drive cable.
12. The rotational IVUS device of claim 11, wherein the polymer
layer is coated with the lubricious coating.
Description
CROSS REFERENCE TO RELATED APPLICATIONS
[0001] The present application is a continuation of U.S. patent
application Ser. No. 14/716,462, filed May 19, 2015, now U.S. Pat.
No. ______, which claims priority to and the benefit of the U.S.
Provisional Patent Application No. 62/000,810, filed May 20, 2014,
which are hereby incorporated by reference in their entireties.
FIELD OF DISCLOSURE
[0002] The present disclosure generally relates to intravascular
devices, such as catheters and guide wires, used in clinical
diagnostic and therapeutic procedures, including intravascular
ultrasound (IVUS) procedures. These intravascular devices can
include a flexible drive cable having a transducer disposed at a
distal end thereof for imaging a vessel of interest. During the
IVUS procedure, the drive cable and the transducer may be rotated
within the intravascular device to allow capturing of multiple
images of the vessel. Embodiments of the present disclosure include
a lubricious coating on the drive cable to promote uniform rotation
of the drive cable and the transducer by reducing rotational
friction experienced by the drive cable. Embodiments of the present
disclosure include radiopaque markers on the drive cable, or
defined by the drive cable, for accurate estimation of lesion
lengths within the body of the patient and for accurate placement
of the transducer within of the vessel.
BACKGROUND
[0003] IVUS imaging procedures are widely used in interventional
cardiology as a diagnostic tool for assessing a vessel, such as an
artery, within the body of the patient to determine the need for
treatment, to guide intervention, and/or to assess the
effectiveness of administered treatment. An IVUS imaging system
uses ultrasound echoes to form a cross-sectional image of the
vessel of interest. Typically, IVUS imaging uses a transducer in a
catheter to emit ultrasound signals (waves) and to receive the
reflected ultrasound signals. The emitted ultrasound signals (often
referred to as ultrasound pulses) pass easily through most tissues
and blood, but they are partially reflected by discontinuities
arising from tissue structures (such as the various layers of the
vessel wall), red blood cells, and other features of interest. The
IVUS imaging system, which is connected to the catheter by way of a
patient interface module, processes the received ultrasound signals
(often referred to as ultrasound echoes) to produce a
cross-sectional image of the vessel proximate to where the catheter
is located.
[0004] The two types of catheters in common use today are
solid-state and rotational. A conventional solid-state catheter may
use an array of transducers (typically 64) distributed around a
circumference of a sheath, which is an outer layer of the catheter.
The transducers are connected to an electronic multiplexer circuit.
The multiplexer circuit selects transducers from the array for
transmitting ultrasound signals and receiving reflected ultrasound
signals. By stepping through a sequence of transmit-receive
transducer pairs, the solid-state catheter can synthesize the
effect of a mechanically scanned transducer element, but without
moving parts. Since there is no rotating mechanical element, the
transducer array can be placed in direct contact with blood and
vessel tissue with minimal risk of vessel trauma, and the
solid-state scanner can be wired directly to the IVUS imaging
system with a simple electrical cable and a standard detachable
electrical connector.
[0005] On the other hand, a conventional rotational catheter may
include a flexible drive cable that continually rotates inside the
sheath of the catheter inserted into the vessel of interest. The
drive cable may have a transducer disposed at a distal end thereof.
The transducer is typically oriented such that the ultrasound
signals propagate generally perpendicular to an axis of the
catheter. In the typical rotational catheter, the sheath may be
filled with fluid (e.g., saline) to protect the vessel tissue from
the rotating drive cable and transducer while permitting ultrasound
signals to freely propagate from the transducer into the tissue and
back. As the drive cable rotates (e.g., at 30 revolutions per
second), the transducer is periodically excited with a high voltage
pulse to emit a short burst of ultrasound. The ultrasound signals
are emitted from the transducer, through the fluid-filled sheath
and sheath wall, in a direction generally perpendicular to an axis
of rotation of the drive cable (i.e., the axis of the IVUS
catheter). The transducer then listens for returning ultrasound
signals reflected from various tissue structures, and the IVUS
imaging system assembles a two dimensional image of the vessel
cross-section from a sequence of several hundred of these
ultrasound pulse/echo acquisition sequences occurring during a
single revolution of the drive cable and the transducer.
[0006] However, the images obtained by the conventional rotational
catheters exhibit distortion caused due to non-uniform rotational
distortion (NURD). The distorted images fail to provide the
required insight into the vessel condition. NURD may occur due to,
for example, friction between the drive cable and the sheath that
encloses the drive cable; friction between the sheath and the
vessels through which the catheter travels through during use;
non-symmetrical drive cable/transducer assembly that causes the
drive cable to resist bending more at some angles than at other
angles (when rotated, these asymmetries cause the drive cable to
store more energy in some angular orientations and then to release
that energy as the drive cable is rotated past that angle); the
sheath and drive cable containing various bends and twists along
its path to the vessel of interest, resulting in the transducer
rotating at a non-uniform angular velocity even though the drive
cable is rotated at a constant speed. As such, the conventional
rotational catheters fail to adequately minimize non-uniform
rotational distortion, while also providing sufficient strength and
flexibility.
[0007] Intravascular devices are also used diagnostically to
measure internal body dimensions, estimate lesion lengths, and to
ensure accurate placement of the intravascular device within the
body of the patient. In several of these procedures, it is
advantageous to be able to visualize the progress of the
transducer, which enables the imaging, towards the target location
within the body of the patient. Introducing intravascular devices
into the body often requires fluoroscopic visualization to aid the
treating healthcare provider in guiding the intravascular device to
the target site. Intravascular devices are commonly formed of a
non-radiopaque polymeric material. Therefore, radiopaque markers
are affixed at a distal end of the intravascular device to enable
the intravascular device to be visualized during x-ray and
fluoroscopic procedures. For example, in intravascular procedures,
health care providers may guide the intravascular device to a
target location by using fluoroscopy to track the position of
radiopaque markers on distal end of the intravascular device.
[0008] Conventionally, these radiopaque markers are circumferential
metallic bands affixed to the exterior surface of the intravascular
device. Although these marker bands allow the distal end of the
intravascular devices to be visualized by fluoroscopy, they present
certain problems. First, affixing of the radiopaque markers to the
exterior surface of the sheath of the catheter fails to provide
guidance as to the accurate position of the included transducer
that enables the imaging within the body of the patient. The
operator is undesirably left to guess or estimate the position of
the transducer during the imaging procedure. Further, metallic
marker bands require affixing (e.g., by crimping, swaging, or
adhesive) to the underlying intravascular device to avoid slippage
as the intravascular device is moved through the body. The bands
may protrude from the tubular surface of the intravascular device
and increase the intravascular device profile, which creates
frictional resistance to the translational movement of the
intravascular device through body passages, and potentially damages
tissues contacting the moving intravascular device. In some
instances, where a marker band has been swaged onto the exterior
surface of the intravascular device, and the inner diameter of a
marker band is greater than the outer diameter of the intravascular
device, buckling may occur, causing the marker band to crack and
the exterior surface to tear. Finally, the placement of band
markers on the outer surface presents problems with inadvertent
disassociation of the markers from the intravascular device, with
attendant loss of positional and measurement accuracy. In addition,
such marker bands are constructed from expensive and heavy
radiopaque metals such as gold, platinum, tantalum, and alloys of
these dense materials. The use of these heavy materials typically
results in inflexible and rigid marker bands that can impair the
trackability of the catheter by increasing the stiffness of the
intravascular device, thereby compromising the flexibility and
maneuverability of the intravascular device. As such, the
conventional intravascular device with radiopaque markers affixed
to the exterior surface fail to enable accurate measurement of
internal body dimensions, accurate estimation of lesion lengths,
and accurate placement of the transducer within the body of the
patient.
[0009] Accordingly, there remains a need for improved ultrasound
intravascular devices for use in IVUS imaging and associated
devices, systems, and methods. The devices, systems, and methods
proposed in the present disclosure overcome one or more of the
deficiencies of conventional intravascular devices.
SUMMARY
[0010] In one aspect, the present disclosure provides a device
including a drive cable to rotate about an axis of rotation
associated with the IVUS device and a transducer coupled to a
distal end of the flexible drive cable such that the transducer
rotates with the drive cable. The drive cable may be a hollow
flexible coil and may be coated with a lubricious coating. The
lubricious coating may be a hydrophobic or a hydrophilic coating or
solution. The drive cable may be coated with the lubricious
material by dipping the drive cable in the lubricious coating, by
rolling the drive cable in the lubricious coating, or by applying
the lubricious coating on the drive cable with a wipe. In one
embodiment, the drive cable may be surrounded by a polymer layer.
The polymer layer can be formed of any suitable material, including
high density polyimide and low density polyimide. The transducer
may be coupled to the flexible drive cable by two or more layers of
counter wound stainless steel wires. The device may include an
interface module to provide, over a rotational interface, a first
control signal to enable rotation of the drive cable, and a second
control signal to regulate operation of the transducer. The device
may also include an integrated circuit (IC) electrically coupled to
the transducer, the IC being located at the distal end of the drive
cable. In one embodiment, the IC may include an amplifier, a
transmitter, and protection circuitry. The device may include a
catheter assembly to at least partially enclose the drive cable.
The catheter assembly may include a polymer layer that surrounds
the drive cable. The drive cable may include a plurality of
radiopaque markers. In some embodiments, the drive cable includes
the plurality of radiopaque markers adjacent to the distal end of
the drive cable, and in another embodiment, the drive cable
includes the plurality of radiopaque markers along a majority or
the entire length of the drive cable. The plurality of radiopaque
markers may be of equal or variable size. Similarly, the plurality
of radiopaque markers may be spaced equidistantly or variably along
the drive cable. In one embodiment, a width of a radiopaque marker
may be substantially equal to or proportional to a distance between
two adjacent radiopaque markers.
[0011] In one aspect, the present disclosure provides a device
including a drive cable to rotate about an axis of rotation
associated with the IVUS device and a transducer coupled to a
distal end of the flexible drive cable such that the transducer
rotates with the drive cable, wherein a polymer layer encloses the
drive cable without enclosing the transducer. In one embodiment,
the polymer layer may be fixedly secured to and surrounding the
drive cable without enclosing the transducer. The device may
contain a catheter assembly that includes the polymer layer, which
may be formed of any suitable material including a polyimide
ethylene, a high density polyimide, or a low density polyimide. In
some embodiments, the polymer may be coated with a lubricious
coating. The lubricious coating may be a hydrophobic or a
hydrophilic coating or solution. Further, the drive cable may
include a plurality of radiopaque markers. In some embodiments, the
drive cable includes the plurality of radiopaque markers adjacent
to the distal end of the drive cable, and in another embodiment,
the drive cable includes the plurality of radiopaque markers along
a majority or the entire length of the drive cable. The plurality
of radiopaque markers may be of equal or variable size. Similarly,
the plurality of radiopaque markers may be spaced equidistantly or
variably along the drive cable. In one embodiment, a width of a
radiopaque marker may be substantially equal to or proportional to
a distance between two adjacent radiopaque markers.
[0012] In another aspect, the present disclosure provides a device
including a drive cable configured to rotate about an axis of
rotation associated with the IVUS device and a transducer coupled
to a distal end of the flexible drive cable such that the
transducer rotates with the drive cable, wherein the drive cable
includes a plurality of radiopaque markers. The plurality of the
radiopaque markers may be flexible to conform to the flexibility of
the drive cable. In some embodiments, the drive cable includes the
plurality of radiopaque markers adjacent to the distal end of the
drive cable, and in another embodiment, the drive cable includes
the plurality of radiopaque markers along a majority or the entire
length of the drive cable. The plurality of radiopaque markers may
be of equal or variable size. Similarly, the plurality of
radiopaque markers may be spaced equidistantly or variably along
the drive cable. In some embodiments, a width of a radiopaque
marker may be substantially equal to or proportional to a distance
between two adjacent radiopaque markers. Further, a first distance
between two adjacent radiopaque markers located at the distal end
of the drive cable may be smaller than a second distance between
two adjacent radiopaque markers located at the proximal end of the
drive cable. The plurality of radiopaque markers provide varying
radiopacity of known dimensions at known distances on the drive
cable to allow accurate placement of the transducer and accurate
measurement of desired anatomical structures.
[0013] In some embodiments, the drive cable may include the
plurality of radiopaque markers in the form of an alternating
series of tightly wound sections and loosely wound sections of the
drive cable. The tightly wound sections may comprise areas of a
closed pitch and the loosely wound sections may comprise areas of
an open pitch. Also, the tightly wound sections may be uniformly or
variably spaced from each other by the loosely wound sections. In
one embodiment, the tightly wound sections and/or the loosely wound
sections may be of respective uniform lengths.
[0014] It is to be understood that both the foregoing general
description and the following detailed description are exemplary
and explanatory in nature and are intended to provide an
understanding of the present disclosure without limiting the scope
of the present disclosure. In that regard, additional aspects,
features, and advantages of the present disclosure will be apparent
to one skilled in the art from the following detailed
description.
BRIEF DESCRIPTION OF THE DRAWINGS
[0015] The accompanying drawings illustrate embodiments of the
devices and methods disclosed herein and together with the
description, serve to explain the principles of the present
disclosure. Throughout this description, like elements, in whatever
embodiment described, refer to common elements wherever referred to
and referenced by the same reference number. The characteristics,
attributes, functions, interrelations ascribed to a particular
element in one location apply to those elements when referred to by
the same reference number in another location unless specifically
stated otherwise.
[0016] The figures referenced below are drawn for ease of
explanation of the basic teachings of the present disclosure only;
the extensions of the figures with respect to number, position,
relationship, and dimensions of the parts to form the following
embodiments will be explained or will be within the skill of the
art after the following description has been read and understood.
Further, the exact dimensions and dimensional proportions to
conform to specific force, weight, strength, and similar
requirements will likewise be within the skill of the art after the
following description has been read and understood.
[0017] The following is a brief description of each figure used to
describe the present disclosure, and thus, is being presented for
illustrative purposes only and should not be limitative of the
scope of the present disclosure.
[0018] FIG. 1 illustrates an exemplary imaging system according to
an embodiment of the present disclosure.
[0019] FIG. 2 illustrates a partial cutaway perspective view of an
exemplary imaging device according to an embodiment of the present
disclosure.
[0020] FIG. 3A and 3B illustrate cross-sectional side views of
portions of exemplary catheters according to embodiments of the
present disclosure.
[0021] FIGS. 4A and 4B illustrate exemplary drive cables according
to embodiments of the present disclosure.
[0022] FIG. 5 illustrates another exemplary drive cable according
to an embodiment of the disclosure.
[0023] FIGS. 6A and 6B illustrate cross-sectional side views the
exemplary drive cable according to embodiments of the present
disclosure.
DETAILED DESCRIPTION
[0024] For the purposes of promoting an understanding of the
principles of the present disclosure, reference will now be made to
the embodiments illustrated in the drawings, and specific language
will be used to describe the same. It will nevertheless be
understood that no limitation of the scope of the disclosure is
intended. Any alterations and further modifications to the
described devices, instruments, methods, and any further
application of the principles of the present disclosure are fully
contemplated as would normally occur to one skilled in the art to
which the disclosure relates. In particular, it is fully
contemplated that the features, components, and/or steps described
with respect to one embodiment may be combined with the features,
components, and/or steps described with respect to other
embodiments of the present disclosure. For the sake of brevity,
however, the numerous iterations of these combinations will not be
described separately. For simplicity, in some instances the same
reference numbers are used throughout the drawings to refer to the
same or like parts.
[0025] As discussed above, there remains a need for improved
ultrasound intravascular devices to be used in IVUS imaging
procedures and associated devices, systems, and methods. The
present disclosure describes devices, systems, and methods to
reduce non-uniform rotational distortion and also to accurately
measure internal body dimensions, accurately estimate lesion
lengths, and accurately place the transducer within the body of the
patient. In particular, the present disclosure provides a
lubricious coating applied to the drive cable to promote uniform
rotation of the drive cable and the transducer by minimizing
non-uniform rotation distortion and by reducing rotational friction
between the rotating drive cable and (i) the fluid filled in the
sheath of the catheter, and/or (ii) the inner surface of the sheath
of the catheter. Further, the present disclosure provides
radiopaque markers on the drive cable (or defined by the drive
cable) to accurately measure internal body dimensions, accurately
estimate lesion lengths, and/or accurately place the transducer
within the body of the patient.
[0026] Referring to FIG. 1, shown therein is an IVUS imaging system
100 according to an embodiment of the present disclosure. The IVUS
system can utilize any type of suitable IVUS imaging device 102,
including rotational and/or phased array based devices. In some
particular embodiments, the present disclosure incorporates a
focusing transducer. The transducer may be a piezoelectric
micromachined ultrasound transducer (PMUT) fabricated on a
microelectromechanical system (MEMS) substrate using a polymer
piezoelectric material, for example as disclosed in U.S. patent
application Ser. No. 13/892,045, filed May 10, 2013, and/or U.S.
Pat. No. 6,641,540, each of which is hereby incorporated by
reference in its entirety. In some embodiments of the present
disclosure, the IVUS imaging system 100 is a PMUT rotational IVUS
imaging system. In that regard, the main components of the PMUT
rotational IVUS imaging system include the PMUT rotational IVUS
catheter 102, a PMUT catheter compatible patient interface module
(PIM) 104, an IVUS console or processing system 106, and a monitor
108 to display the IVUS images generated by the IVUS console 106.
Generally, the catheter 102 may be configured to take on any
desired arcuate profile when in the curved configuration. In one
instance, the catheter 102 may have an overall length of at least
90 cm, and in some embodiments, extending to 150 cm. Larger lengths
of the catheter 102 are also contemplated. Also, the catheter 102
may have an external diameter ranging from 2 F to 9 F (i.e., 0.67
mm to 3 mm). As discussed in greater detail below, the PMUT
rotational IVUS catheter 102 includes a PMUT ultrasound transducer
along with its associated circuitry mounted near a distal tip of
the catheter and the appropriate electrical connector to support
the rotational interface. The PMUT-compatible PIM 104 generates
and/or provides the required sequence of transmit trigger signals
and control waveforms to regulate the operation of the circuit and
processes the amplified echo signals received over that same
conductor pair. The PMUT-compatible PIM 104 also supplies the high-
and low-voltage DC power supplies to support operation of the PMUT
rotational IVUS catheter 102. The PMUT-compatible PIM 104 allows
delivery of DC supply voltages to the PMUT circuitry of the
catheter 102 across a rotational interface. This feature largely
precludes the requirement of a rotary transformer, commonly used
for traditional rotational IVUS systems, since a transformer can
only convey AC signals from the primary to the secondary side.
Practical options for delivering DC power across a rotating
interface include the use of slip-rings and/or the implementation
of the active spinner technology described in U.S. Patent
Application Publication No. 2010/0234736, which is hereby
incorporated by reference in its entirety.
[0027] Referring now to FIG. 2, shown therein is a diagrammatic,
partial cutaway perspective view of the PMUT catheter 102 according
to an embodiment of the present disclosure. In that regard, FIG. 2
shows additional detail regarding the construction of the PMUT
rotational IVUS catheter 102. In many respects, this catheter is
similar to traditional rotational IVUS catheters, such as the
Revolution.RTM. catheter available from Volcano Corporation and
described in U.S. Pat. No. 8,104,479, or those disclosed in U.S.
Pat. Nos. 5,243,988 and 5,546,948, each of which is hereby
incorporated by reference in its entirety. In that regard, the PMUT
rotational IVUS catheter 102 includes an imaging core 110 and an
outer catheter/sheath assembly 112. The imaging core 110 includes a
flexible drive cable 132 that is terminated at the proximal end by
a rotational interface 114 providing electrical and mechanical
coupling to the PIM 104 of FIG. 1. As such, the drive cable 132 is
at least partially enclosed in the catheter/sheath assembly 112.
The distal end of the flexible drive cable 132 of the imaging core
110 is coupled to a transducer housing 116 containing the PMUT and
associated circuitry, which are described in greater detail below.
The catheter/sheath assembly 112 includes a hub 118 that supports
the rotational interface and provides a bearing surface and a fluid
seal between the rotating and non-rotating elements of the catheter
assembly. The hub 118 includes a luer lock flush port 120 through
which saline is injected to flush out the air and fill the inner
lumen of the sheath with an ultrasound-compatible fluid at the time
of use of the catheter. The saline or other similar flush is
typically required since air does not readily conduct ultrasound.
Saline also provides a biocompatible lubricant for the rotating
drive cable. The hub 118 is coupled to a telescope 122 that
includes nested tubular elements and a sliding fluid seal that
permit the catheter/sheath assembly 112 to be lengthened or
shortened to facilitate axial movement of the transducer housing
within an acoustically transparent window 124 of the distal portion
of the catheter 102. In some embodiments, the window 124 includes
thin-walled plastic tubing fabricated from material(s) that readily
conduct ultrasound waves between the transducer and the vessel
tissue with minimal attenuation, reflection, or refraction. A
proximal shaft 126 of the catheter/sheath assembly 112 bridges the
segment between the telescope 122 and the window 124, and includes
a material or composite that provides a lubricious internal lumen
and optimum stiffness, but without the need to conduct
ultrasound.
[0028] Referring now to FIG. 3A, shown therein is a cross-sectional
side view of a distal portion of the catheter 102 according to an
embodiment of the present disclosure. In particular, FIG. 3A shows
an expanded view of aspects of the distal portion of the imaging
core 110. In this exemplary embodiment, the imaging core 110 is
terminated at its distal tip by a housing 116 fabricated from
stainless steel and provided with a rounded nose 126 and a cutout
128 for the ultrasound beam 130 to emerge from the housing 116. In
some embodiments, the flexible drive cable 132 of the imaging core
110 includes two or more layers of counter wound stainless steel
wires, welded, or otherwise secured to the housing 116 such that
rotation of the flexible drive cable also imparts corresponding
rotation on the housing 116. In the illustrated embodiment, the
PMUT MEMS 138 includes a spherically focused transducer 142 and
carries an application-specific integrated circuit (ASIC) 144. The
ASIC 144 is electrically coupled to the PMUT MEMS 138 through two
or more connections. In that regard, in some embodiments of the
present disclosure the ASIC 144 includes an amplifier, a
transmitter, and a protection circuit associated with the PMUT
MEMS. In some embodiments, the ASIC 144 is flip-chip mounted to the
substrate of the PMUT MEMS 138 using anisotropic conductive
adhesive or suitable alternative chip-to-chip bonding method. When
assembled together the PMUT MEMS 138 and the ASIC 144 form an
ASIC/MEMS hybrid assembly 146 that is mounted within the housing
116. An electrical cable 134 with optional shield 136 is attached
to the ASIC/MEMS hybrid assembly 146 with solder 140. The
electrical cable 134 extends through an inner lumen of the flexible
drive cable 132 to the proximal end of the imaging core 110 where
it is terminated to the electrical connector portion of the
rotational interface 114 shown in FIG. 2. In an embodiment, the
length of the typical electrical cable 134 may range from 120.0 cm
to 200.0 cm. The ASIC/MEMS hybrid assembly 146 may be secured in
place relative to the housing 116 by an epoxy 148 or other bonding
agent. The epoxy 148 may also serve as an acoustic backing material
to absorb acoustic reverberations propagating within the housing
116 and as a strain relief for the electrical cable 134 where it is
soldered to the ASIC/MEMS hybrid assembly 146.
[0029] In an exemplary embodiment, the drive cable 132 may be a
hollow flexible coil. The drive cable 132 may be coated with a
lubricious coating 170. The drive cable 132 may be coated by, for
example, dipping the drive cable 132 in the lubricious coating 170,
by rolling the drive cable 132 in the lubricious coating 170, or by
applying the lubricious coating 170 on the drive cable 132 with,
for example, a wipe. In one embodiment, the lubricious coating 170
may be adhered to the drive cable 132 by using ultra-violet (UV)
intensity, and may be used in conjunction with or along with a
primer. The lubricious coating 170 may be a hydrophilic or
hydrophobic solution. Further, the lubricious coating 170 may be a
water-based or a solvent-based coating.
[0030] The lubricious coating may have very low frictional
properties to promote uniform rotation of the drive cable 132 and
the transducer 142 by reducing any static or dynamic frictional
forces experienced by the rotating drive cable 132. For example,
the lubricious coating 170 may substantially reduce the surface
energy interactions between the rotating drive cable 132 and the
inner walls of the sheath 112 and/or any fluid positioned
therebetween. Applying the lubricious coating directly to the
rotating drive cable 132 reduces and/or eliminates NURD and allows
the drive cable 132 and the transducer 142 to predictably rotate at
a more uniform angular velocity even when the rotating drive cable
132 comes in contact with the surrounding surfaces. Also, the
reduction in friction assists in expediting the imaging procedure
and in minimizing patient trauma.
[0031] Referring now to FIG. 3B, shown therein is a cross-sectional
side view of a distal portion of the catheter 102 according to an
embodiment of the present disclosure. The catheter 102 illustrated
in FIG. 3B is identical with respect to the catheter 102
illustrated in FIG. 3A except that the catheter 102 illustrated in
FIG. 3B includes a polymer layer 160. The polymer layer 160 may be
fixedly secured to the drive shaft 132 so that it is positioned
between the sheath 112 and the imaging core 110 to facilitate
low-friction, uniform rotation of the drive cable transducer 142.
The polymer layer 160 can be formed of a material having less
friction than the drive cable 132. For example, the polymer layer
160 may include high-density polyimide ethylene (HDPE) material,
low-density polyimide ethylene (LDPE) material, or polyimide
ethylene (PE) material. The polymer layer 160 may also include
nylon, pebax, or any other common metric material. In some
embodiments, the polymer layer 160 is coated with the lubricious
coating 170 to further reduce any frictional forces with respect to
the polymer layer 160 and the surrounding sheath and/or fluids.
[0032] FIG. 4A illustrates an exemplary drive cable 132 according
to an embodiment of the disclosure. The drive cable 132 may include
a plurality of radiopaque markers 140. In one embodiment, a
predetermined number of individual coils of the drive cable 132,
which are separated by a predetermined distance, may be coated with
radiopaque material to induce radiopaque markers 140 on the drive
cable 132. In another embodiment, the radiopaque markers may be
circumferential bands, having predetermined widths, affixed on the
outer surface of the drive cable 132 at predetermined distances.
These circumferential bands may also be flexible to conform to the
flexibility of the drive cable 132. The radiopaque markers may be
separate elements fixedly secured to the drive cable.
[0033] In one embodiment, the drive cable 132 may include the
plurality of radiopaque markers 140 at a distal end of the drive
cable 132. In another embodiment, the drive cable 132 may include
the plurality of radiopaque markers 140 along a majority or the
entire length of the drive cable 132. The radiopaque markers may be
of equal or variable size and may be placed equidistantly or
variably along the drive cable 132. In that regard, each radiopaque
marker may have a predetermined width (W) ranging from 0.5 mm to
1.0 cm and may be placed at a predetermined distance(s) (D) ranging
from 1.0 mm to 150.0 cm. In some embodiments, the width W of the
radiopaque markers may be substantially the same as the spacing
distance D, but in other embodiments, the width W may vary in
accordance with the desired application for the radiopaque markers.
In one embodiment, the width W may be proportional to the distance
D. Also, as illustrated in FIG. 4B, the radiopaque markers may be
placed at varying distances based on their location on the drive
cable 132. For example, a first distance (D1) between the
radiopaque markers at the distal end of the drive cable 132 may be
smaller than a second distance (D2) between the radiopaque markers
at a more proximal location along the length of the drive cable
132. The distance D1 may range from 1.0 mm to 10.0 cm and the
distance D2 may range from 1.0 cm to 50.0 cm. In another
embodiment, the distances between the radiopaque markers may
progressively decrease from the proximal end to the distal end of
the drive cable 132.
[0034] As discussed above, the present disclosure proposes affixing
radiopaque markers to the drive cable 132 (instead of the exterior
surface of the sheath of the catheter) for accurately placing the
transducer within the body of the patient. It is advantageous to
affix the radiopaque markers to the drive cable 132 because this
enables the operator to accurately observe and track the position
of the transducer 142, relative to the known positions of the
radiopaque markers 140 on the drive cable, once the catheter 102 is
inserted in the body of the patient. The knowledge of the accurate
position of the transducer 142 allows accurate placement of the
transducer 142 at the desired locations within the vessel of
interest for imaging. This reduces instances where an operator must
guess or estimate the location of the transducer 142 in the
catheter 102 during the imaging procedure. As such, the overall
efficiency of the imaging procedure is increased. Further, affixing
the radiopaque markers to the drive cable 132 enables accurately
measuring internal body dimensions, and accurately estimating
lesion lengths. In particular, the strategically designed placement
of the radiopaque markers of known dimensions at known distances
along the length of the drive cable 132 allows the operator to use
the radiopaque markers to accurately measure internal body
dimensions and lesion lengths. The accurate measurement of these
anatomical structures may assist the health care provider in
diagnosing a condition, deciding on the appropriate course of
treatment, treating the condition, and evaluating the results of
the treatment. The radiopaque markers can also be utilized to track
the position of the intravascular device and/or the transducer to
facilitate co-registration of the images obtained with the
intravascular device to other types of intravascular or
extravascularly obtained patient data.
[0035] Additional advantages may be realized by affixing the
radiopaque markers to the drive cable 132. In particular, the drive
cable 132 does not come in direct contact with the body passages
since the drive cable 132 is surrounded by fluid and the sheath 112
of the catheter 102. As such, any instance of trauma to the body
tissue is minimized even if the radiopaque markers protrude or
buckle because the protrusions would be contained by the sheath
112. Also, the risk of disassociation of the radiopaque markers
from the drive cable 132 due to friction with the bodily passages
is minimal for the same reason that the drive cable 132 is
surrounded by low friction fluid. Therefore, affixing the
radiopaque markers directly to the drive cable 132 again increases
the overall efficiency and safety of the imaging procedure.
[0036] FIG. 5 illustrates another exemplary drive cable 132
according to an embodiment of the disclosure. In this embodiment,
the drive cable 132 may define radiopaque markers in the form of
tightly wound sections 150 separated by the loosely wound sections
152. The drive cable 132 may be formed of a single length of
material that has been wound into areas of varying pitch and coated
with a radiopaque material. Alternatively, the entire portion of
the drive cable 132 defining the radiopaque markers can be formed
of a radiopaque material. The radiopaque material may be one or
more radiopaque metals including, but not limited to, gold,
tungsten, iridium, rhodium, platinum, barium, bismuth, and
combinations and/or alloys thereof. In some embodiments, the
radiopaque material is a radiopaque polymer, which may comprise a
matrix of a polymeric material in combination with a radiopaque
metal. Any material with a high enough radiodensity when shaped
into a tightly wound section 150 can be used. For example, the
drive cable 132 may be formed of lower cost alternatives to
precious metals with equivalent radiodensity.
[0037] The tightly wound sections 150 are tightly wound areas of
the drive cable 132 that form blocks of greater radiopacity or
radiodensity with respect to the loosely wound sections 152. As
such, the tightly wound sections of the radiopaque element are
ultrasonically recognizable to the imaging device. In some
embodiments, the tightly wound sections 150 have a width (W)
ranging from 1.0 mm to 2.0 mm. Both the tightly wound sections 150
and the loosely wound sections 152 retain the ability to flex. The
tightly wound sections 150 may have greater widths W (and greater
resultant visibility) than rigid, metallic marker bands. Thus, the
tightly wound sections 150 form flexible radiopaque markers that
are capable of curving with the catheter 102 as it traverses
through tortuous anatomy without causing the inadvertent catheter
kinking and/or trauma that can be caused by rigid marker bands.
[0038] The tightly wound sections 150 have a closed pitch while the
loosely wound sections 152 have an open pitch. In other words, the
tightly wound sections 150 are formed of tightly compressed
individual coils 154 of the drive cable 132 having little to no
space between them, while the loosely wound sections 152 are formed
by coils 154 having greater space between centers of adjacent coils
154. In some embodiments, the pitch of the coils 154 in the loosely
wound sections 152 may range from 1.1938 mm (0.047 inches) to
1.3462 mm (0.053 inches). In the pictured embodiment, the loosely
wound sections 152 are formed by four loosely wound turns or coils
154 of the drive cable 132. However, the loosely wound sections 152
may be formed by any number of coils 154.
[0039] In one embodiment, the drive cable 132 is manufactured by
stretching a tightly compressed coil at constant intervals past the
recovery point of the coil material, thereby creating alternating
areas of tightly wound coil and loosely wound coil. Stretching the
coil past its recovery point "sets" the intervals between the
individual coils (e.g., coils 154) and creates constant intervals
between the tightly wound sections 150 and the loosely wound
sections 152. For example, in the pictured embodiment in FIG. 5,
the tightly wound sections 150 are separated from one another by a
constant interval I1, which reflects a fixed distance between
adjacent tightly wound sections 150. The individual coils 154 of
the loosely wound sections 152 are separated from one another by a
constant interval 12, which reflects a fixed distance between
adjacent loosely wound coils 154 in the loosely wound sections 152.
The interval I1 may vary in different embodiments depending upon
the particular application desired. For example, in various
embodiments, the interval I1 may range from 0.5 cm to 5 cm. In some
embodiments, the interval I1 of the drive cable 132 is 1 cm. Thus,
the drive cable 132 has highly radiopaque tightly wound sections
150 alternating with less radiopaque loosely wound sections 152 at
substantially constant intervals, allowing the drive cable 132 to
serve as an internal marking or measuring device. In some
embodiments, the drive cable 132 may be wound around a hollow and
flexible tubular member to prevent unwanted kinking of the drive
cable, while maintaining flexibility. In some embodiments, the
hollow, flexible member may have a uniform diameter and may include
a proximal portion and a distal portion with a central lumen
extending therebetween.
[0040] In some embodiments, the drive cable 132 incorporating the
plurality of radiopaque markers is coated with a lubricious coating
170 and/or surrounded by a polymer layer as described above in the
context of FIGS. 3A, 3B, 4A, and 4B. For example, FIG. 6A
illustrates a cross-sectional side view of a portion of the drive
cable 132 according to an embodiment of the present disclosure
where the drive cable 132 includes a plurality of radiopaque
markers 140, as discussed with respect to FIGS. 4A, 4B, and 5, and
is coated with a lubricious coating 170 to reduce rotational
frictional forces experienced by the drive cable 132. As another
example, FIG. 6B illustrates a cross-sectional side view of a
portion of the drive cable 132 according to another embodiment of
the present disclosure where the drive cable 132 includes a
plurality of radiopaque markers 140, as discussed with respect to
FIGS. 4A, 4B, and 5, and is surrounded by a polymer layer 160,
which may or may not be coated with a lubricious coating 170, to
reduce the rotational frictional forces experienced by the drive
cable 132.
[0041] Embodiments in accordance with the present disclosure
provide users with an accurate and efficient device, system, and
method for evaluating, localizing, and measuring anatomical
structures and/or lesions to plan an appropriate treatment course
and/or evaluate a given treatment. For example, but not by way of
limitation, embodiments of the present disclosure may be used to
assist in evaluating an intraluminal site for implantation of a
prosthesis (e.g., a drug-eluting balloon, a drug-eluting stent, a
stent graft, a bioresorbable stent), PTCA balloon location, an
endovascular aneurysm repair (e.g., of the abdominal or thoracic
aorta), IVC filter placement (e.g., in the inferior vena cava),
evaluation of tumor growth/response to treatment, and a variety of
other procedures previously utilizing a separate measuring device
(e.g., a ruler) for lesion measurement. In addition, embodiments of
the present disclosure may be used to monitor the position and/or
efficacy of already implanted devices such as, but not by way of
limitation, stents, stent grafts, drug-eluting stents, drug-eluting
balloons, and orthopedic implants (e.g., bone screws or hip,
shoulder, or knee implants). Moreover, the present disclosure can
eliminate at least one pigtail marker catheter exchange in several
procedures, such as a low contrast endovascular aneurysm repair
procedure, thereby accelerating the process of stent-graft length
sizing assessment. Some embodiments of the present disclosure may
be used in a variety of organ systems such as, but not by way of
limitation, the circulatory system, the lymphatic system, the
digestive system, the pulmonary system, the orthopedic system, and
the neurological system.
[0042] Persons of ordinary skill in the art will appreciate that
the embodiments encompassed by the present disclosure are not
limited to the particular exemplary embodiments described above. In
that regard, although illustrative embodiments have been shown and
described, a wide range of modification, change, and substitution
is contemplated in the foregoing disclosure. It is understood that
such variations may be made to the foregoing without departing from
the scope of the present disclosure. Accordingly, it is appropriate
that the appended claims be construed broadly and in a manner
consistent with the present disclosure.
* * * * *