U.S. patent application number 15/065498 was filed with the patent office on 2016-06-30 for therapeutic ultrasound system.
The applicant listed for this patent is FLOWCARDIA, INC.. Invention is credited to Henry Nita.
Application Number | 20160183956 15/065498 |
Document ID | / |
Family ID | 38576304 |
Filed Date | 2016-06-30 |
United States Patent
Application |
20160183956 |
Kind Code |
A1 |
Nita; Henry |
June 30, 2016 |
THERAPEUTIC ULTRASOUND SYSTEM
Abstract
An ultrasound system has a catheter including an elongate
flexible catheter body having at least one lumen extending
longitudinally therethrough. An ultrasound transmission wire
extends longitudinally through the lumen of the catheter body, and
has a proximal region, a distal region, and an intermediate region
between the proximal region and the distal region. A sonic
connector is connected to the proximal region of the ultrasound
transmission wire, and a distal head is positioned at the distal
end of the catheter body and coupled to the distal region of the
ultrasound transmission wire. The proximal region of the ultrasound
transmission wire has a larger diameter than the intermediate
region, the intermediate region is continuously tapered with a
progressively decreasing diameter from its proximal end to its
distal end, and the distal region has a greater diameter than the
distal end of the intermediate region.
Inventors: |
Nita; Henry; (Redwood
Shores, CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
FLOWCARDIA, INC. |
Tempe |
AZ |
US |
|
|
Family ID: |
38576304 |
Appl. No.: |
15/065498 |
Filed: |
March 9, 2016 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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11398385 |
Apr 5, 2006 |
9282984 |
|
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15065498 |
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Current U.S.
Class: |
604/22 ;
606/128 |
Current CPC
Class: |
A61B 2017/22001
20130101; A61B 17/22012 20130101; A61B 2017/00477 20130101; A61B
2217/007 20130101; A61B 2017/22082 20130101 |
International
Class: |
A61B 17/22 20060101
A61B017/22 |
Claims
1. An ultrasound catheter comprising: an elongate flexible catheter
body having a proximal end, a distal end and at least one
longitudinal lumen; an ultrasound transmission wire extending
through the lumen, the ultrasound transmission wire having a first
proximal region, a second region, a distal region, and an
intermediate region between the second region and the distal
region; a sonic connector connected to and surrounding the first
proximal region; and a distal head positioned at the distal end and
coupled to the distal region; wherein the first proximal region has
a larger diameter than the second region, the second region has a
larger diameter than the intermediate region, the intermediate
region continuously tapers with a progressively decreasing diameter
from its proximal end to its distal end, and the distal region has
a greater diameter than the distal end of the intermediate
region.
2. The catheter of claim 1 wherein the intermediate region has a
plurality of progressively tapered sections, each tapered section
having a distal end and a proximal end, with each tapered section
having a diameter that progressively decreases from its proximal
end to its distal end.
3. The catheter of claim 2 wherein the distal-most end of the
ultrasound transmission wire extends beyond the distal-most end of
the catheter body.
4. The catheter of claim 3 wherein the ultrasound transmission wire
is made of a super-elastic metal alloy.
5. The catheter of claim 4 wherein the ultrasound transmission wire
has a circular configuration over its entire length.
6. The catheter of claim 5 wherein the first proximal region of the
ultrasound transmission wire has the greatest diameter.
7. A method for disrupting an occlusion in a blood vessel
comprising the steps of: positioning an ultrasound catheter in a
blood vessel such that a distal end of the catheter is adjacent an
occlusion; introducing refrigerated irrigation fluid through the
catheter; and transmitting ultrasound energy through the ultrasound
catheter to disrupt the occlusion into multiple occlusion
fragments.
8. The method of claim 7 wherein positioning the ultrasound
catheter comprises using a guiding catheter.
9. The method of claim 8 wherein positioning the ultrasound
catheter comprises using a guidewire.
10. The method of claim 7 wherein positioning the ultrasound
catheter comprises using a guidewire.
11. The method of claim 10 further including removing the occlusion
fragments through the ultrasound catheter.
12. The method of claim 11 further including: providing an
irrigation inlet aperture at a proximal end of the catheter; and
introducing irrigation fluid through the aperture.
13. The method of claim 12 further including providing an
irrigation outlet aperture at a distal end of the catheter.
14. The method of claim 13 wherein the irrigation outlet aperture
includes a side hole on the distal end of the catheter.
15. The method of claim 13 wherein the irrigation outlet aperture
includes a side-hole aperture at the distal end of the catheter and
an outlet through the tip of the ultrasound catheter.
16. The method of claim 15 wherein the refrigerated irrigation
fluid temperature is below 72 degrees Fahrenheit.
17. The method of claim 16 wherein the refrigerated irrigation
fluid temperature is between 40 and 72 degrees Fahrenheit.
18. The method of claim 17 wherein the refrigerated irrigation
fluid is delivered during the delivery of ultrasound energy.
19. The method of claim 18 wherein the refrigerated irrigation
fluid is delivered during an interventional procedure.
20. The method of claim 19 wherein the irrigation fluid contains a
pharmacological agent.
Description
PRIORITY
[0001] This application is a division of U.S. application Ser. No.
11/398,385, filed Apr. 5, 2006, now U.S. Pat. No. 9,282,984, which
is incorporated by reference in its entirety into this
application.
FIELD OF THE INVENTION
[0002] The present invention pertains to medical equipment, and
more particularly, to a therapeutic ultrasound system for ablating
obstructions within tubular anatomical structures such as blood
vessels.
BACKGROUND
[0003] A number of ultrasound systems and devices have heretofore
been proposed for use in ablating or removing obstructive material
from blood vessels. However, all of these systems and devices
generally encounter three types of problems which are not always
adequately addressed by these systems and devices.
[0004] One type of problem relates generally to the effective
transmission of ultrasound energy from an ultrasound source to the
distal tip of the device where the ultrasound energy is applied to
ablate or remove obstructive material. Since the ultrasound source,
such as a transducer, is usually located outside the human body, it
is necessary to deliver the ultrasound energy over a long distance,
such as about 150 cm, along an ultrasound transmission wire from
the source to the distal tip. Attenuation of the acoustical energy
along the length of the transmission wire means that the energy
reaching the distal tip is reduced. To ensure that sufficient
energy reaches the distal tip, a greater amount of energy must be
delivered along the transmission wire from the source to the distal
tip. This transmission of increased energy along the transmission
wire may increase the fatigue experienced by the transmission wire
at certain critical locations, such as at the connection between
the transducer and the transmission wire. This fatigue and any
associated stress may cause the transmission wire to break.
[0005] In this regard, the size of the proximal end of the
transmission wire cannot be large. The proximal end of the
transmission wire is usually bent while moving the ultrasound
catheter back and forth during interventional procedures. A larger
proximal end for a transmission wire will cause higher attenuation
than a smaller proximal end, and provides a larger mass to expand
and contract during the delivery of ultrasound energy.
[0006] Another type of problem relates to the heat that is built up
from the transmission of ultrasound energy along the transmission
wire. Many ultrasound transmission wires are made of superelastic
alloys which exhibit elasticity within a specific temperature
range, usually between 10 degrees Celsius and 50 degrees Celsius.
However, during the delivery of ultrasound energy, the temperature
of the transmission wire may reach 100 to 200 degrees Celsius, at
which the transmission wire may lose its superelasticity and may
experience mechanical deformations at portions that are bent when
exposed to the high temperatures. The high temperatures may also
cause the propagated energy to be lost more rapidly and transferred
to heat, thereby reducing the efficacy of the ultrasound
transmission wire.
[0007] Conventional ultrasound systems typically infuse a coolant
fluid (usually 0.9% NaCI solution) through the irrigation lumen of
an ultrasound catheter to bathe the transmission wire. To maintain
the transmission wire within the desired temperature range of 10-50
degrees Celsius, the irrigation rate of the coolant fluid needs to
be dramatically increased. However, there are two limitations to
this approach. First, endovascular catheters usually have small
inner and outer diameters that range between 0.5 to 3 mm.
Therefore, the volume of fluid that can be delivered through the
catheter is relatively small. Second, there is a limit to the
amount of irrigant that can be delivered and left in the body of
the patient during any interventional procedure, and this amount of
irrigant should not exceed 500-1,000 cm3. In addition to these two
limitations, increased irrigation fluid pressure may cause local
tissue damage.
[0008] Thus, there still exists a need in the art for improved
ultrasound systems having ultrasound devices or catheters which
address the aforementioned problems.
SUMMARY
[0009] It is an object of the present invention to provide an
improved transmission wire for an ultrasound device.
[0010] It is another object of the present invention to provide an
improved way of cooling the transmission wire of an ultrasound
device during an interventional procedure.
[0011] In order to accomplish the objects of the present invention,
there is provided an ultrasound system having a catheter including
an elongate flexible catheter body having at least one lumen
extending longitudinally therethrough. An ultrasound transmission
wire extends longitudinally through the lumen of the catheter body,
and has a proximal region, a distal region, and an intermediate
region between the proximal region and the distal region. A sonic
connector is connected to the proximal region of the ultrasound
transmission wire, and a distal head is positioned at the distal
end of the catheter body and coupled to the distal region of the
ultrasound transmission wire. The proximal region of the ultrasound
transmission wire has a larger diameter than the intermediate
region, the intermediate region is continuously tapered with a
progressively decreasing diameter from its proximal end to its
distal end, and the distal region has a greater diameter than the
distal end of the intermediate region.
[0012] The present invention also discloses a method for disrupting
an occlusion in a blood vessel, which includes positioning an
ultrasound catheter in a blood vessel such that a distal end of the
catheter is adjacent an occlusion, introducing refrigerated
irrigation fluid through the catheter, and transmitting ultrasound
energy through the ultrasound catheter to disrupt the occlusion
into multiple occlusion fragments.
[0013] The present invention also discloses a method for disrupting
an occlusion in a blood vessel, which includes positioning an
ultrasound catheter in a blood vessel such that a distal end of the
catheter is adjacent the occlusion, transmitting ultrasound energy
through the ultrasound catheter to disrupt the occlusion into
multiple occlusion fragments, and introducing microbubbles around
the distal end of the catheter during the transmission of
ultrasound energy.
DRAWINGS
[0014] FIG. 1 is a perspective view of an ultrasound system
according to the present invention.
[0015] FIG. 2 is a cross-sectional view of the distal end of an
ultrasound catheter that can be used with the system of FIG. 1.
[0016] FIG. 3 is a side sectional view of an ultrasound
transmission wire that can be used with the system of FIG. 1.
[0017] FIG. 4 is a cross-sectional view of the proximal end of the
catheter of FIG. 2 showing the connection of the ultrasound
transmission wire of FIG. 3 to a sonic connector.
[0018] FIG. 5 is a side view of the catheter of FIG. 2.
[0019] FIG. 6 is a cross-sectional view of the sonic connector of
the system of FIG. 1.
DETAILED DESCRIPTION
[0020] The following detailed description is of the best presently
contemplated modes of carrying out the invention. This description
is not to be taken in a limiting sense, but is made merely for the
purpose of illustrating general principles of embodiments of the
invention. The scope of the invention is best defined by the
appended claims.
[0021] In certain instances, detailed descriptions of well-known
devices, compositions, components, mechanisms and methods are
omitted so as to not obscure the description of the present
invention with unnecessary detail.
[0022] FIGS. 1 and 2 illustrate an ultrasound system according to
the present invention for use in ablating and removing occlusive
material inside the vessel of an animal or human being. The
ultrasound system includes an ultrasound catheter device 10 which
has an elongate catheter body 12 having a proximal end 14, a distal
end 16, and defining at least one lumen 40 extending longitudinally
therethrough. The ultrasound catheter device 10 is operatively
coupled at its proximal end 14, by way of a Y-connector 18, a
catheter knob 20, and a slide collar 22, to an ultrasound
transducer 24. The ultrasound transducer 24 is connected to a
signal generator 26, which can be provided with a foot actuated
on-off switch 28. The signal generator 26 can be supported by an IV
pole 27. When the on-off switch 28 is depressed, the signal
generator 26 sends an electrical signal to the ultrasound
transducer 24, which converts the electrical signal to ultrasound
energy. Such ultrasound energy subsequently passes through the
catheter device 10 and is delivered to the distal end 16. A
guidewire 30 may be utilized in conjunction with the catheter
device 10, as will be more fully described below.
[0023] The catheter body 12 is formed of a flexible polymeric
material such as nylon (Pebax.TM.) manufactured by Atochimie, Cour
be Voie, Hauts Ve-Sine, France. The flexible catheter body 12 is
preferably in the form of an elongate tube having one or more
lumens extending longitudinally therethrough. The catheter body 12
defines a main lumen 40. Extending longitudinally through the main
lumen 40 is an elongate ultrasound transmission wire 42 having a
proximal end which is removably connectable to the ultrasound
transducer 24 via a sonic connector 76 (described below in
connection with FIGS. 4 and 6) such that ultrasound energy will
pass through the ultrasound transmission member 42. As such, when
the foot actuated on-off switch 28 operatively connected to the
ultrasound transducer 24 is depressed, ultrasound energy will pass
through the ultrasound transmission member 42 to the distal end 16
of the catheter body 12.
[0024] A distal head 44 is affixed to the distal end 16 of the
catheter body 12. In the embodiments shown, the distal head 44 has
a generally blunt distal tip 46, and has a proximal portion 48
whose outer diameter is slightly less than the largest outer
diameter of the distal head 44, so as to define an annular shoulder
50 that is placed in the open distal end of the catheter body 12
such that the proximal portion 48 of the distal head 44 is received
inside the catheter body 12 in a manner where the outer surface of
the catheter body 12 is flush with the outer surface of the distal
head 44.
[0025] A guidewire port 58 is provided in the catheter body 12 at a
location that is about 0.1 cm to 30 cm from the distal head 44. A
guidewire lumen 60 extends from the guidewire port 58 through a
bore 62 in the distal head 44 to a guidewire exit 64 at the tip 46
of the distal head 44.
[0026] The distal head 44 is preferably formed of a material that
is rigid, is radio-dense, and has low-density. A material having
such characteristics is desirable because the ultrasound energy
that is delivered from a transducer 24 to the distal head 44 via
the ultrasound transmission member 42 goes through severe bends in
the patient's vasculature. These bends significantly impact the
displacement at the distal head 44 and its ability to ablate
atherosclerotic plaque. The distal head 44 provides an additional
load so that a heavier distal head 44 will cause lower
displacements. As a result, a distal head 44 made of a material
that is rigid, is radio-dense, and which has low-density will
improve the effectiveness of the ablation. As a non-limiting
example, the material should have an average density that does not
exceed 5 g/cm3, or where the total mass of the distal head 44 does
not exceed 0.015 grams.
[0027] As for the desired materials for the distal head 44,
titanium alloys are preferable because they have the highest
strength-to-weight ratios of any structural metals, and are
corrosion resistant and biocompatible. Pure titanium has a density
of 0.163 lb/in3. Examples of desirable alloy elements for use with
Titanium include Aluminum and Vanadium, such as in Ti--6AI-4V,
which has tensile yield strength in the range of 130-150 ksi.
[0028] Although pure Aluminum is relatively weak, alloying with
various elements yields significant strength improvements with
minimal sacrifice in density. Pure Aluminum has a density of 0.097
lb/in3. Examples of desirable alloying elements for Aluminum
include Manganese, Silicon, and/or Magnesium, such as in 3, 4, 5
and 6 series Aluminum alloys. Tensile yield strengths of these
common alloys range from 10-50 ksi.
[0029] Magnesium alloys are also preferable because they are
extremely light, stable, abundant, and easy to machine. They have
high specific strength and rigidity, with a very low density range
of 0.064-0.066 lb/in3, and UTS range of 22-55 ksi. Examples of
desirable alloying elements that can be used with Magnesium include
Aluminum and Zinc, such as in AZ31B for machined tips.
[0030] The ultrasound transmission wire 42 extends through the
lumen 40, and is inserted into a bore 52 which extends
longitudinally into the proximal portion 48 of the distal head 44.
The distal end of the ultrasound transmission wire 42 is firmly
held within the bore 52 by the frictional engagement thereof to the
surrounding material of the distal head 44, or by other mechanical
or chemical affixation means such as but not limited to weldments,
adhesive, soldering and crimping. Firm affixation of the ultrasound
transmission wire 42 to the distal head 44 serves to facilitate
direct transmission of the quanta of ultrasonic energy passing
through the ultrasound transmission wire 42 to the distal head 44.
As a result, the distal head 44 and the distal end 16 of the
catheter device 10 are caused to undergo ultrasonic vibration in
accordance with the combined quanta of ultrasonic energy being
transmitted through the ultrasound transmission wire 42.
[0031] In the preferred embodiment, the ultrasound transmission
wire 42 may be formed of any material capable of effectively
transmitting the ultrasonic energy from the ultrasound transducer
24 to the distal head 44, including but not necessarily limited to
metal, plastic, hard rubber, ceramic, fiber optics, crystal,
polymers, and/or composites thereof. In accordance with one aspect
of the invention, all or a portion of the ultrasound transmission
wire 42 may be formed of one or more materials which exhibit
super-elasticity. Such materials should preferably exhibit
super-elasticity consistently within the range of temperatures
normally encountered by the ultrasound transmission wire 42 during
operation of the catheter device 10. Specifically, all or part of
the ultrasound transmission wire 42 may be formed of one or more
metal alloys known as "shape memory alloys".
[0032] Examples of super-elastic metal alloys which are usable to
form the ultrasound transmission wire 42 of the present invention
are described in detail in U.S. Pat. Nos. 4,665,906 (Jervis);
4,565,589 (Harrison); 4,505,767 (Quin); and 4,337,090 (Harrison).
The disclosures of U.S. Pat. Nos. 4,665,906; 4,565,589; 4,505,767;
and 4,337,090 are expressly incorporated herein by reference
insofar as they describe the compositions, properties, chemistries,
and behavior of specific metal alloys which are super-elastic
within the temperature range at which the ultrasound transmission
wire 42 of the present invention operates, any and all of which
super-elastic metal alloys may be usable to form the super-elastic
ultrasound transmission wire 42.
[0033] The frontal portion of the Y-connector 18 is connected to
the proximal end 14 of the catheter 10 using techniques that are
well-known in the catheter art. An injection pump 54 or IV bag (not
shown) or syringe (not shown) can be connected, by way of an
infusion tube 55, to an infusion port or sidearm 72 of the
Y-connector 18 (see FIG. 1). The injection pump can be used to
infuse coolant fluid into and/or through the main lumen 40 of the
catheter 10, with the coolant fluid exiting via irrigation outlets
56 (see FIGS. 2 and 5) provided adjacent the distal end 16 of the
catheter 10. Such flow of coolant fluid may be utilized to prevent
overheating of the ultrasound transmission wire 42 extending
longitudinally through the main lumen 40. Such flow of the coolant
fluid through the main lumen 40 of the catheter 10 also serves to
bathe the outer surface of the ultrasound transmission wire 42,
thereby providing for an equilibration of temperature between the
coolant fluid and the ultrasound transmission wire 42. Thus, the
temperature and/or flow rate of coolant fluid may be adjusted to
provide adequate cooling and/or other temperature control of the
ultrasound transmission wire 42. The irrigation fluid can include a
pharmacological agent.
[0034] According to one embodiment of the present invention, the
coolant fluid is preferably a refrigerated coolant fluid,
preferably saline 0.9% NaCI. The refrigerated coolant fluid will be
stored in a refrigerator or similar cooling unit at a temperature
between 4 and 20 degrees Celsius (or between 40-72 degrees
Fahrenheit) prior to use. The use of a low-temperature coolant
fluid will be effective in maintaining the transmission wire 42
within the desired temperature range of 10-50 degrees Celsius. The
refrigerated coolant fluid can be flowed through the main lumen 40
and exit the catheter body 12 via irrigation outlets 56 (see FIGS.
2 and 5) provided adjacent the distal end 16 of the catheter 10 and
through the irrigation outlet 65 in the distal head 44. The numeral
designation 66 in FIG. 2 can be used to represent the refrigerated
coolant fluid and the microbubbles described below.
[0035] In addition to the foregoing, the injection pump 54 or
syringe may be utilized to infuse a radiographic contrast medium
into the catheter 10 for purposes of imaging, as described in
greater detail below. Examples of iodinated radiographic contrast
media which may be selectively infused into the catheter 10 via the
injection pump are commercially available as Angiovist 370 from
Berlex Labs, Wayne, N.J. and Hexabrix from Malinkrodt, St. Louis,
Mo.
[0036] The proximal end of the Y-connector 18 is attached to the
distal end of the catheter knob 20 by threadably engaging the
proximal end of the Y-connector 18 inside a threaded distal bore
(not shown) at the distal end of the catheter knob 20.
[0037] Referring also to FIGS. 4 and 6, the present invention
further provides a sonic connector assembly that effectively
connects the ultrasound transmission wire 42 to the transducer 24
in a manner which reduces step sonic amplification and provides a
smooth connection transition of the transmission wire 42, thereby
reducing the stress and fatigue experienced by the transmission
wire 42. The sonic connector assembly includes a sonic connector 76
that functions to grip or otherwise retain the proximal end of the
ultrasound transmission wire 42, and which can be removably
connected to the transducer 24. In other words, the sonic connector
76 serves as an attaching element that couples the ultrasound
transmission wire 42 to the transducer 24 in a manner which
minimizes transverse movement at the connection area while
maintaining longitudinal ultrasound energy propagation. In this
regard, longitudinal vibrations are desirable, while transverse
vibrations may cause breakage in the ultrasound transmission wire
42. The connection area between the ultrasound transmission wire 42
and the transducer horn 78 is critical because the vibrational
energy passes through this connection. At this highest displacement
point, longitudinal vibrations produce antinodes (maximum
displacement/minimum stress), while transverse vibrations produce a
node or area of maximum stress. Since the greatest amount of
transverse motion occurs at the connection area between the
ultrasound transmission wire 42 and the transducer horn 78, and
because the cross-section of the ultrasound transmission wire 42 is
small, reduction of transverse movements at the connection area
between the ultrasound transmission wire 42 and the transducer horn
78 is crucial in protecting the integrity of the ultrasound
transmission wire 42 and minimizing the potential for breakage of
the ultrasound transmission wire 42. Such transverse vibrations can
be minimized by placing transverse absorbers along the ultrasound
transmission wire 42 at the connection area between the ultrasound
transmission wire 42 and the transducer horn 78, as described
below.
[0038] The sonic connector 76 is housed inside the proximal bore 84
of the catheter knob 20. The proximal bore 84 has a proximal
opening into which the transducer horn 78 may be inserted to engage
the sonic connector 76. A distal bore 88 is provided at the distal
end of the catheter knob 20, with the distal bore 88 communicating
with the proximal bore 84 via a channel 90. The sonic connector 76
has a front shaft 94 extending distally from a central portion 92.
The sonic connector 76 also has a threaded stem 96 extending
proximally from the central portion 92 to permit the distal end of
the transducer horn 78 to be threadably screwed onto and removably
attached to the sonic connector 76. The proximal end of the
Y-connector 18 can be threadably engaged to the distal opening of
the distal bore 88.
[0039] The distal end of the front shaft 94 has an inner bore (not
shown) that terminates before the central portion 92. The proximal
portion of the ultrasound transmission wire 42 extends through the
channel 90 in the knob 20 and through the bores 84 and 88, and the
proximal-most region 421 is dimensioned to be snugly fitted inside
the inner bore of the front shaft 94. The proximal-most region 421
of the ultrasound transmission wire 42 is secured inside the inner
bore of the front shaft 94 by welding, bonding, crimping,
soldering, or other conventional attachment mechanisms.
[0040] A first absorber 98 is seated in the distal bore 88 and
itself defines a bore that receives (i.e., circumferentially
surrounds) the ultrasound transmission wire 42. In other words, the
absorber 98 is positioned between the ultrasound transmission wire
42 and the bore 88. The absorber 98 can be made of an elastic
material, and non-limiting examples include a polymer or rubber.
Alternatively, the absorber 98 can be provided in the form of
0-rings. The absorber 98 functions to absorb transverse
micro-motions, thereby minimizing the undesirable transverse
vibrations.
[0041] The sonic connector 76 can be provided with a partial thread
and a flat proximal surface, which are important to providing a
firm connection between the transducer horn 78 and the sonic
connector 76. Specifically, referring to FIGS. 4 and 6, the
threaded stem 96 has a thread 102 followed by a small unthreaded
area 104 that separates the thread 102 from the proximal surface
106 of the central portion 92. This proximal surface 106 is flat,
and interfaces with the flat distal surface of the transducer horn
78 (see FIG. 4), thereby allowing a manual connection and
disconnection (screw and unscrew) between the transducer horn 78
and the sonic connector 76.
[0042] The present invention provides an ultrasound transmission
wire 42 having a configuration that improves the delivery of
ultrasound energy to the distal head 44 while minimizing stress and
fatigue at the connection of the ultrasound transmission wire 42 to
the sonic connector 76. In particular, the ultrasound transmission
wire 42 of the present invention provides a proximal-most end that
is connected with the sonic connector 76, with this proximal-most
end having a greater diameter than the rest of the ultrasound
transmission wire 42.
[0043] The ultrasound transmission wire 42 has a first
proximal-most region 421, a second region 422 that extends distally
from the distal end of the first region 421, a third region 423
that extends distally from the distal end of the second region 422,
a fourth region 424 that extends distally from the distal end of
the third region 423, a fifth region 425 that extends distally from
the distal end of the fourth region 424, a sixth region 426 that
extends distally from the distal end of the fifth region 425, and a
seventh distal-most region 427 that extends distally from the
distal end of the sixth region 426. As best shown in FIG. 2, the
distal-most region 427 is received into the bore 52 of the distal
head 44. The fourth region 424 and the fifth region 425 together
define an intermediate region 428. The first region 421 has a
diameter that is greater than the diameter of any of the other
regions 422, 423, 424, 425, 426, 427, and the diameter of the first
region 421 can be consistent throughout. The diameter of the second
region 422 progressively tapers and decreases from its proximal end
(where it transitions from the first region 421) to its distal end,
where it transitions to the third region 423. The diameter of the
third region 423 can be consistent throughout. The distal end of
the third region 423 transitions to the proximal end of the
intermediate region 428. The diameter of the intermediate region
428 progressively tapers and decreases from its proximal end (where
it transitions from the third region 423) to its distal end, where
it transitions to the sixth region 426. In this regard, the
intermediate region 428 can be made up of any number of
progressively decreasing-diameter regions itself, and the
embodiment of FIG. 4 illustrates that the intermediate region 428
is made up of two such regions, the fourth region 424 and the fifth
region 425. Thus, the diameter of the intermediate region 428 is
smallest at its distal end (see 429), and in fact, the diameter at
the distal end 429 of the intermediate region 428 can be the
smallest along the length of the entire ultrasound transmission
wire 42. The length of the intermediate region 428 is preferably
between 5 to 150 cm, depending on the desired application. For
example, the length of the region 428 can be about 40 cm if the
catheter 10 is for use in coronary applications, and about 90 cm if
the catheter 10 is for use with peripheral applications. Next, the
diameter of the sixth region 426 progressively increases from its
proximal end (where it transitions from the intermediate region
428) to its distal end, where it transitions to the seventh region
427. The diameter of the seventh region 427 can be consistent
throughout. The diameter throughout the seventh region 427 is
greater than the diameter of any part of the sixth region 426. In
one embodiment of the present invention, the entire ultrasound
transmission wire 42 (including all of its regions 421-427) can be
formed in a single piece.
[0044] The first proximal-most region 421 is adapted to be attached
to the sonic connector 76, which is in turn attached to the
transducer 24. The first region 421 has a length that ranges
between 0.005 and 5 inches, but is preferably between 0.01 and 0.5
inches. The first region 421 has a cross-sectional outer diameter
that ranges between 0.01 and 0.06 inches, but is preferably between
0.035 and 0.045 inches. The third region 423 has a cross-sectional
outer diameter that ranges between 0.02 and 0.05 inches, but is
preferably about 0.030 inches. The third region 423 has a length
that ranges between 20 to 140 cm, and preferably about 100 cm.
[0045] The significance of a larger-diameter proximal-most region
421 that is adapted to connect to the sonic connector 76 is as
follows. The difference between the dimensions of the ultrasound
transmission wire 42 and the horn of the transducer 24 creates a
dimensional step which causes a large amplification of propagated
ultrasound energy from the transducer 24 via the sonic connector 76
to the ultrasound transmission wire 42. In fact, both the
transverse and longitudinal motions produced by the transducer 24
will be amplified by this dimensional step. In particular, the
transverse motions create significant stress at the connection area
between the ultrasound transmission wire 42 and the transducer 24.
As a result, a smaller ultrasound transmission wire 42 (i.e.,
having a smaller diameter) would be more susceptible to breakage at
the connection area. However, providing a larger-diameter
ultrasound transmission wire 42 would not be feasible. For example,
the proximal 10 to 20 inches of the ultrasound transmission wire 42
will typically be outside the patient during an interventional
procedure, and this proximal portion is often subjected to bends
while a physician handles the catheter 10. These bends would cause
a larger-diameter ultrasound transmission wire 42 to experience
greater acoustical losses than a smaller-diameter ultrasound
transmission wire 42. As a result of these considerations, the
present invention provides a novel configuration for the ultrasound
transmission wire 42 where (i) the proximal-most region 421 has the
greatest diameter to minimize breakage at the connection area, (ii)
portions of the intermediate region 428 (e.g., the region 425) have
the smallest diameter to improve propagation of ultrasound energy,
and (iii) the distal regions 426, 427 have a greater diameter than
the intermediate region 428 to facilitate greater efficiency in the
transmission of ultrasound energy from the ultrasound transmission
wire 42, to improve the strength of the ultrasound transmission
wire 42, and to minimize breakage of the ultrasound transmission
wire 42. In particular, increasing the cross-section of the
ultrasound transmission wire 42 at its distal end provides a larger
cross-sectional area to tolerate stress associated with the
attachment of distal-most region 427 to the distal head 44.
[0046] The tapering in some of the regions (e.g., 423, 424, 425,
426) provides a continuous and smooth transition for the
amplification of ultrasound energy without steps, which helps
improve the stability of the ultrasound transmission wire 42.
[0047] The present invention also provides the use of microbubbles
to enhance the cavitational effect and improve the ultrasound
ablation. According to the present invention, microbubbles 66 (see
FIG. 2) can be injected with a cooling fluid or irrigant during an
ultrasound procedure when ultrasound energy is being delivered to
the distal head 44. The microbubbles 66 that can be used in the
present invention can be embodied in the form of agitated saline
solution, or made of gas encapsulated in shells. Examples of
commercially available microbubbles include but are not limited to
OPTISON.TM. sold by Mallincrodt Medical, DEFINITY.TM. sold by
Dupont Pharmaceuticals, LEVOVIST.TM. and IMAGENT.TM. sold by
Schering, SONO VUE.TM. sold by Bracco Imaging, and PB-127.TM. sold
by Point-Biomedical. The microbubbles 66 can be introduced through
the infusion port or sidearm 72 of the Y-connector 18 by an
injection pump. The microbubbles 66 are delivered into and/or
through the main lumen 40 of the catheter 10 and exit via
irrigation outlets 56 (see FIGS. 2 and 5) provided adjacent the
distal end 16 of the catheter 10 and through the irrigation outlet
65 in the distal head 44. The microbubbles 66a can also be
delivered in front of the distal head 44 via a conventional guiding
catheter 67 (see FIG. 2) or any other sheath that surrounds the
catheter 10.
[0048] The microbubbles 66, 66a improve the cavitational effect. In
particular, the reciprocating movement of the distal tip 46 of the
catheter 10 in a fluid (i.e., blood) creates cavities or bubbles to
create a transitory phenomenon or mechanical effect called
cavitation. It produces an instantaneous stress estimated at many
thousands of atmospheres, and a significantly higher temperature
within a cavitation threshold, at a very small area in front of the
distal tip 46. If the catheter is placed against atherosclerotic
material, this cavitation will cause ablation of the material.
Adding microbubbles 66, 66a in front of the distal tip 46 where
cavitation is taking place will increase the number of bubbles at
the distal tip 46, thereby enhancing cavitation. In other words,
the introduction of additional microbubbles increases the
cavitational effect without changing or adding to the construction
of the catheter 10.
[0049] Thus, the ultrasound system according to present invention
provides structural components that address two of the general
problems encountered by the known ultrasound systems and devices.
For instance, effective transmission of ultrasound energy is
achieved by the novel transmission wire 42 and the sonic connector
76. In addition, the transmission wire 42 is cooled by the
refrigerated coolant fluid and the use of microbubbles. Further,
the introduction of microbubbles to the distal tip 46 of the
catheter 10 enhances cavitation.
[0050] While the description above refers to particular embodiments
of the present invention, it will be understood that many
modifications may be made without departing from the spirit
thereof. The accompanying claims are intended to cover such
modifications as would fall within the true scope and spirit of the
present invention.
* * * * *