U.S. patent application number 10/071197 was filed with the patent office on 2003-04-24 for implantable electro-acupuncture device.
Invention is credited to Malaney, James, Nelson, Randy.
Application Number | 20030078642 10/071197 |
Document ID | / |
Family ID | 23815879 |
Filed Date | 2003-04-24 |
United States Patent
Application |
20030078642 |
Kind Code |
A1 |
Malaney, James ; et
al. |
April 24, 2003 |
Implantable electro-acupuncture device
Abstract
Improved implantable devices for electro-acupuncture are
described. The devices include a flexible conductor electrode, an
anchor fixation for preventing motion of the device in tissue after
implantation, and/or a sealed, liquid-impermeable housing.
Inventors: |
Malaney, James; (Iowa City,
IA) ; Nelson, Randy; (Pine Springs, MN) |
Correspondence
Address: |
DORSEY & WHITNEY LLP
INTELLECTUAL PROPERTY DEPARTMENT
50 SOUTH SIXTH STREET
MINNEAPOLIS
MN
55402-1498
US
|
Family ID: |
23815879 |
Appl. No.: |
10/071197 |
Filed: |
February 7, 2002 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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10071197 |
Feb 7, 2002 |
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09457217 |
Dec 9, 1999 |
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6377853 |
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Current U.S.
Class: |
607/115 |
Current CPC
Class: |
A61N 1/3787 20130101;
A61N 1/36017 20130101; A61H 39/002 20130101; A61N 1/0551 20130101;
A61N 1/0558 20130101; A61N 1/36071 20130101 |
Class at
Publication: |
607/115 |
International
Class: |
A61N 001/05 |
Claims
What is claimed is:
1. An implantable electro-acupuncture device, comprising: an
elongate, flexible conductor for applying an electric charge to a
predetermined tissue locus, the conductor having a proximal end and
a distal portion, the distal portion having a distal tip; a housing
secured to the proximal end of the conductor; and an electrical
source for providing an electric current to the conductor, the
electrical source being disposed within the housing and in
electrical connection with the conductor.
2. The implantable electro-acupuncture device of claim 1, wherein
the conductor comprises at least one wire.
3. The implantable electro-acupuncture device of claim 1, wherein
the device further comprises an insulator surrounding at least a
portion of the conductor.
4. The implantable electro-acupuncture device of claim 1, wherein
the electrical source comprises a receiver for receiving external
signals, and a converter for converting the external signals to
electrical impulses to supply electric current to the
conductor.
5. The implantable electro-acupuncture device of claims 4, wherein
converter comprises at least one inductive coil.
6. The implantable electro-acupuncture device of claim 4, wherein
the signals are effective to control at least one variable with
respect to the electrical impulses.
7. The implantable electro-acupuncture device of claim 6, wherein
the at least one variable is selected from the group consisting of
pulse width, pulse sequence, pulse interval and pulse power.
8. The implantable electro-acupuncture device of claim 3, wherein
the conductor is electrically insulated from the housing.
9. The implantable electro-acupuncture device of claim 8, wherein
the conductor is coated with an insulating layer, and wherein at
least a portion of the distal tip is exposed though the insulating
layer.
10. The implantable electro-acupuncture device of claim 1, wherein
the conductor is an electrically conducting cable.
11. The implantable electro-acupuncture device of claim 10, wherein
the cable is comprised of a plurality of flexible, multi-stranded
cable bundles.
12. The implantable electro-acupuncture device of claim 1, wherein
the housing is secured to the proximal end of the conductor via a
connection element.
13. The implantable electro-acupuncture device of claim 12, wherein
the connection element is a crimp connector.
14. The implantable electro-acupuncture device of claim 12, further
comprising a protective member connected to the housing such that
the protective member encloses the connection element.
15. The implantable electro-acupuncture device of claim 14, wherein
the protective member is a strain relief boot.
16. The implantable electro-acupuncture device of claim 14, wherein
the protective member is made of a biocompatible material.
17. The implantable electro-acupuncture device of claim 16, wherein
the biocompatible material is an insulating.
18. The implantable electro-acupuncture device of claim 17, wherein
the material is selected from the group consisting of silicone and
polyurethane.
19. The implantable electro-acupuncture device of claim 1, further
comprising a securing member, the securing member being positioned
between the housing and the tissue locus and being effective to
secure the housing to the tissue locus, the securing member
comprising: a plurality of lobes, wherein a cavity is defined in
each lobe to form a plurality of suture sites, and wherein a
plurality of suture threads secure the housing to the tissue site,
a first end of each suture thread being sutured to the tissue site
at each suture site and a second end of each suture thread being
sutured to the housing.
20. The implantable electro-acupuncture device of claim 1, further
comprising: an anchor disposed on the conductor, the anchor being
effective to fix the conductor at the predetermined tissue locus to
substantially inhibit movement of the conductor relative to the
predetermined tissue locus.
21. The implantable electro-acupuncture device of claim 20, wherein
the anchor comprises at least one fixation ring disposed about the
conductor.
22. The implantable electro-acupuncture device of claim 20, wherein
the anchor comprises a helical tissue-engaging member disposed at
the distal portion of the conductor.
23. The implantable electro-acupuncture device of claim 1, wherein
the housing comprises a fluid-tight enclosure.
24. The implantable electro-acupuncture device of claim 23, wherein
the housing is hermetically sealed.
25. The device of claim 23, wherein the housing comprises an upper
housing portion and a lower housing portion, the upper and lower
housing portions being secured together in a fluid-tight relation,
and wherein the lower housing portion is also secured to the
conductor.
26. The device of claim 25, wherein the upper housing portion is
secured to the lower housing portion by welding.
27. The device of claim 25, wherein the lower housing portion
comprises a feedthrough effective to provide electrical continuity
between the conductor and the electrical source.
28. An implantable nerve stimulation device, comprising: a housing
which defines a cavity; an electrical current source disposed
within the cavity; a flexible conductor in electrical communication
with the electric current source, the conductor having a proximal
end and a distal portion, the proximal end being secured to the
housing, the distal portion including a distal tip end effective to
apply an electric current to a predetermined tissue locus, the
distal portion further including an anchor effective to fix the
conductor at the predetermined tissue locus to substantially
inhibit movement of the conductor relative to the predetermined
tissue locus; and a second electrode in electrical connection with
the electrical current source to receive the electric current that
has passed through the predetermined tissue locus.
Description
BACKGROUND OF THE INVENTION
[0001] The technical field of this invention is electro-stimulation
of tissue in vivo for therapeutic purposes.
[0002] The use of acupuncture to relieve pain and produce other
therapeutic results has been common in certain cultures for many
years, but only recently has this practice gained a significant
following in the United States. The increased recognition of the
utility of acupuncture in medicine has led to new forms of
acupuncture therapy such as electro-acupuncture, in which the
acupuncture needle is connected to a power source to deliver an
electric current to an acupuncture point. Electro-acupuncture has
the potential to combine the benefits of conventional acupuncture
with the advantages of electrical nerve stimulation.
[0003] Such new acupuncture practices require the development of
devices and methods suitable for safe, reliable delivery of an
electric current via an implantable needle. Implantable
electro-acupuncture devices have been described (e.g., U.S. Pat.
Nos. 5,094,242 and 5,211,175 to Gleason et al.). However, although
these devices solve many of the problems associated with prior art
devices for electrical stimulation, they may not be suitable for
long-term implantation due to the possibility that their needles
will move or shift within tissue, thereby removing the needles from
the desired site of electrical stimulation over time. Moreover, the
relatively inflexible needle of previous devices may not be able to
accommodate a full range of tissue motion, with the accompanying
risk of metal fatigue and eventual fracture of the needle or other
device components, and possible damage to surrounding tissue.
Furthermore, prior art devices often fail due to corrosion or
short-circuits that occur as a result of the infiltration of body
fluids into the device over time.
SUMMARY OF THE INVENTION
[0004] Improved implantable devices for electro-acupuncture and
electrical stimulation having one or more flexible electrodes for
delivering an electric impulse to tissue are herein disclosed.
These devices may also include anchoring mechanisms for preventing
motion of the conductor electrode relative to tissue, and/or may
have sealed, liquid-tight housings. The implantable devices of the
invention are suitable for implantation in a patient's tissue for
extended time periods.
[0005] In one aspect, the invention provides an implantable nerve
stimulation device which includes a housing which defines a cavity,
a source of electrical current disposed within the cavity, a first
electrode for applying an electric current to tissue, and a second
electrode in electrical connection with the source of electric
current for receiving the electric current after the current has
passed through tissue. The second electrode is in electrical
communication with the source of electric current, and, preferably,
is secured to the housing at a proximal end of the first electrode.
The first electrode can be a flexible conductor, having a distal
end adapted for conducting an electric impulse to the tissue.
[0006] In another aspect, the invention provides an implantable
nerve stimulation device which includes a housing which defines a
cavity, a source of electrical current disposed within the cavity,
a first electrode for applying an electric current to tissue, and a
second electrode in electrical connection with the source of
electric current for receiving the electric current after the
current has passed through tissue. The second electrode is in
electrical communication with the source of electric current, has a
distal end for applying an electrical current to tissue, and is
secured to the housing at a proximal end of the first electrode.
The first electrode further includes an anchor for fixing the
distal end of the first electrode relative to the tissue and for
resisting movement within the tissue.
[0007] In still another aspect, the invention relates to an
implantable nerve stimulation device which includes a housing which
defines a cavity, a source of electrical current disposed within
the cavity, a first electrode for applying an electric current to
tissue, and a second electrode in electrical connection with the
source of electric current for receiving the electric current after
the current has passed through tissue. The second electrode is in
electrical communication with the source of electric current, and
is secured to the housing at a proximal end of the first electrode.
The housing is hermetically sealed to prevent ingress of body
fluids into the cavity. The hermetically sealed housing may, for
example, consist in part of a ceramic lid that allows high
frequency energy to pass without being attenuated as with a
comparable metal housing.
[0008] The implantable nerve stimulation device may also include a
protective member, such as a strain relief boot, to protect the
interface between the housing and the conductor, and/or may include
a securing mechanism to suture a portion of the device to tissue in
order to deter or prevent movement of the device from its site of
implantation.
[0009] In any of the above aspects of the invention, an internal
power source may act as the source of electrical current, wherein
the internal power source can be activated and deactivated
remotely.
BRIEF DESCRIPTION OF THE DRAWINGS
[0010] FIG. 1 is a longitudinal cross-sectional, side view of an
electro-acupuncture device of the invention;
[0011] FIG. 1A is a circuit diagram for an illustrative electrical
source for use in the invention;
[0012] FIG. 2 is a cross-sectional, end view of a conductor element
of the device, viewed along the direction of arrows II-II of FIG.
1;
[0013] FIG. 3 is a longitudinal, cross-sectional, side view of an
alternate embodiment of the device of FIG. 1 with an anchor
disposed at the distal portion of the device;
[0014] FIG. 3A is a front view of the anchor of FIG. 3;
[0015] FIG. 4 is a longitudinal, cross-sectional, side view of
another alternate embodiment of the device of FIG. 1 with an
alternate anchor disposed at the distal portion of the device;
[0016] FIG. 5A is longitudinal, cross-sectional, side view of yet
another alternate embodiment of the device of claim 1; and
[0017] FIG. 5B is longitudinal, cross-sectional, side view of still
another alternate embodiment of the device of claim 1; and
[0018] FIG. 6 is a top view of an exemplary tie-down mechanism of
FIG. 5A or 5B.
DETAILED DESCRIPTION OF THE INVENTION
[0019] This invention relates to the field of electro-acupuncture
devices, and particularly to implantable devices for electrical
stimulation of nerves.
[0020] In FIG. 1, an implantable electro-acupuncture device 10 is
shown including a housing 22, and conductor 30 for electrically
stimulating tissue. The conductor 30 passes through an opening 24
in the housing 22 using either a lateral or tangential interface
method. Inside the housing 22 is a voltage or current source 26 for
providing an electrical stimulus to the conductor 30. As shown
schematically in FIG. 1A, source 26 can be a receiver 12 coupled to
an inductive coil 14 in electrical connection with the conductor
electrode 30. For further details regarding the source, see, for
example, U.S. Pat. No. 5,094,242. In this embodiment, the receiver
can receive radio-frequency signals from an external antenna
connected to an external generator-transmitter; the inductive coil
converts the received signal to an electrical impulse which is
supplied to the tissue through the conductor 30. The signals
provided by the external generator-transmitter can determine the
pulse width, the sequence and interval of pulses, and the power of
pulses which are provided by electrical source 26 and thus provided
to the tissue of the patient. Alternatively, source 26 can include
a battery and electrical circuitry for providing a current to the
conductor. In this embodiment, the source 26 can include additional
circuitry for providing electrical impulses; the circuitry can be
configured to permit a variety of pulse widths, pulse trains, power
levels, and the like, depending upon the particular therapeutic
requirements of the patient. In this embodiment, the parameters of
the electrical pulses to be provided by the device 10 to the
patient's tissue can be pre-set prior to implantation of the
device; or the source 26 can alternatively be provided with a
controller for re-setting the parameters after implantation of the
device. For example, the controller can further include a receiver
which can receive commands from an external antenna and be
reprogrammed in response to the received commands to alter the
characteristics of the electrical pulses.
[0021] The housing 22 is electrically coupled to one terminal of
the source 26. In a preferred embodiment, housing 22 is constructed
of an electrically conducting material such as titanium or
stainless steel, as described in more detail below. Alternatively,
the housing 22 can be constructed of a non-conducting (insulating)
material, provided that an electrode is provided to complete the
electrical circuit between the conductor 30 and one terminal of the
source 26. For example, housing 22 can be constructed from an
insulating material such as a biocompatible plastic or ceramic,
with a ring electrode (not shown) embedded in and extending through
the plastic shell and providing an electrical contact with tissue
and with electric voltage or current source 26.
[0022] To prevent short circuits, conductor 30 is generally
electrically insulated from contact with housing 22. If housing 22
is constructed of an electrically conducting material, electrical
insulation between the housing 22 and conductor 30 can be provided
by coating the conductor with an insulating material, such as
Teflon, or by inserting the conductor 30 through a plug of a
suitable dielectric material to provide insulation between the
conductor and the housing. In preferred embodiments, the conductor
30 is coated or covered with a suitable biocompatible insulating
layer 32 along a substantial portion of the longitudinal extent of
the conductor 30, leaving only the distal tip 38 of the conductor
30 in electrical connection with the tissue when the device 10 is
implanted. The insulating layer 32 can be a layer or combination of
layers of, e.g., silicone, polyurethane or
poly(tetrafluoroethylene) (PTFE), or any other biocompatible
electrically insulator known to those of skill in the art.
[0023] The conductor 30 is preferably constructed of materials
which permit the conductor 30 to flex or deform generally according
to the movement of tissues which surround the implantable device 10
when the device is surgically implanted. Thus, the conductor 30 is
preferably constructed of an electrically conducting cable or coil.
The material selected for construction of the conductor 30 should
have an electrical conductivity sufficient to permit the electrical
impulses provided by electrical source 26 to pass through the
conductor 30 without unwanted resistive heating of the conductor 30
or the surrounding tissue. In one preferred embodiment, the
conductor 30 is configured as a multi-stranded cable, as shown in
cross-sectional view in FIG. 2. In the embodiment shown in FIG. 2,
the cable 34 includes smaller multi-stranded cables 39 which can be
twisted together to form cable 34. Such a stranded cable can
provide sufficient electrical conductivity while maintaining
flexibility of the conductor 30. Other flexible conductive cables
which are suitable for use in the present invention will be
apparent to the ordinarily skilled artisan.
[0024] Returning to the description of FIG. I, the conductor 30 can
be formed of a unitary conductor cable, or conductor 30 can be
formed of conductive sections which are secured to each other in
electrical connection. Thus, for example, in the embodiment shown
in FIG. 1, the conductor 30 comprises a conductive cable 34, which
is secured to the housing 22 through a crimp connection 36. Both
the cable portion 34 and the crimp 36 are covered with insulating
layer 32. The conductor 30 also includes an electrically conductive
tip portion 38, which is crimped to the cable portion 34. Tip
section 38 contacts the tissue of the patient and supplies
electrical impulses from electrical source 26 to the tissue. Tip
section 38 may be a variety of shapes including, but not limited
to, pointed and substantially rounded.
[0025] In preferred embodiments, the conductor 30 is provided with
an anchor to reduce or eliminate relative motion between the distal
(non-insulated) portion of the conductor (e.g., tip 38) and the
patient's tissue. By reducing motion of the conductor tip with
respect to tissue, the possibility that the conductor may cause
tissue scarring or damage can be decreased. Moreover, by reducing
the probability that the tip will move away from the desired target
site or nerve, the probability that the device will, over time,
move and thereby fail to provide an electrical impulse to the
correct location in tissue, is reduced. Motion of the conductor tip
after implantation can be reduced by providing the conductor tip
with an anchor for engaging tissue. For example, FIG. 3 depicts a
passive fixation anchor 40, which has the form of a ridge or flange
which extends around all or part of the distal portion 41 of the
conductor 30. The anchor 40 can engage and become entrapped in
tissue, and resist movement through the tissue, thereby decreasing
motion of the conductor 30 in the tissue. However, in a preferred
embodiment, the anchor is configured, in size or shape, to allow
removal of the conductor 30 from tissue, e.g., to permit surgical
removal of the device 10 when therapy is discontinued. The
anchoring ridge or flange can be integrally formed with a portion
of the conductor 30 or the insulation layer 32 (e.g., the anchor
can be formed of an insulating polymer), or the anchor can be a
separate portion which is fixed to the conductor, e.g., by
cementing or welding. As shown in FIG. 3A, the anchor can include
one or more bores 42 that facilitate the placement and/or removal
of the anchor. When the device 10 is surgically implanted within
the patient's tissue, the anchor can be placed at a desired
location within the tissue to ensure proper placement of the
conductor.
[0026] An alternative fixation anchor is shown in FIG. 4. In this
embodiment, the anchor 40' has the form of a helical
tissue-engaging member, such as a wire or coil, which can be turned
or rotated to engage the tissue. In this embodiment, placement of
the device 10 (e.g., by a surgeon) is accomplished by siting the
conductor 30 at the desired location and turning or rotating the
helical member 40' (which can rotate with the conductor or can be
rotatably secured to the conductor to permit separate rotation of
the helical member while the conductor remains stationary) until
the helical member engages tissue to stabilize the conductor tip
against motion relative to the tissue. To facilitate placement by
the physician, the helical member can be covered or otherwise
prevented from engaging tissue during the initial implantation of
the device 10; the cover can be removed to permit the helical
member to engage tissue once the implant 10 is positioned in the
desired location. In a preferred embodiment, the helical member is
configured, in size or shape, to allow removal of the conductor 30
from tissue, e.g., to permit surgical removal of the device 10 when
therapy is discontinued.
[0027] Referring again to the embodiment of FIG. 1, the housing 22
of the device 10 contains the electrical circuitry and components
necessary to provide electrical impulses to the patient's tissue,
as described above. To avoid damage to the electrical components of
the device, the housing 22 is preferably sealed to prevent liquids,
such as body fluids, from contacting the interior of the housing.
The housing preferably is sealed to prevent intrusion of liquids
into the housing even after an extended period of implantation,
e.g., after 1 month, 2 months, 3 months, 6 months, one year or
longer period of implantation. As previously described, it is also
preferable to construct at least a portion of the housing 22 of an
electrically-conductive material, to permit the surface of the
housing to serve as a counter electrode for completing an
electrical circuit in combination with the conductor 30. By
providing a large surface area, an electrically conductive housing
serves as a large counter electrode, reducing the amount of current
to which surrounding, non-target tissues are exposed.
[0028] Thus, in a preferred embodiment, the housing 22 is at least
partially formed of an electrically-conductive material, and is
sealed in liquid-tight sealing relation with the conductor 30. The
conductive housing 22 can be formed of, e.g., titanium,
biocompatible-grade stainless steel, or other conductors which have
sufficient conductivity, biocompatibility, and resistance to attack
by body fluids or tissues. The housing 22 can be provided by
sealing together two components of the housing (e.g., two halves of
the housing), with the electronic elements sealed inside and in
electrical contact with the housing. The housing components can be
welded together (e.g., by laser or Tungsten inert gas welding) to
provide a liquid-tight seal between the components. As previously
described, the housing 22 has a pass-through opening 24 which
permits electrical contact of the current source 26 with the
flexible conductor 30. The opening 24 can comprise a ferrule (not
shown) welded to the housing 22. The opening 24 may be covered with
a suitable material, such as silicone, to prevent liquid and access
and ingress and to provide mechanical strength. If the housing 22
is formed of an electrically-conductive material, the conductor 30
must be electrically insulated from the housing. This result can be
achieved by providing a sealing insulator such a ceramic, glass,
sapphire, non-conductive plastics, and the like.
[0029] Referring now to FIGS. 5A and 5B, an alternate embodiment of
the implantable nerve stimulation device of FIG. 1 is shown. The
device 10 of FIGS. 5A and 5B generally has identical components as
described with respect to FIGS. 1 and 2, and also may utilize
either of the fixation anchors described in FIGS. 3, 3A and 4. As
shown in FIGS. 5A and 5B, however, the device 10 may also include a
protecting member 50 to protect the interface between the housing
22 and the conductor 30, and/or a securing mechanism 60 to suture a
portion of the device 10' to a tissue site to prevent or deter
movement of the device from the tissue site.
[0030] The protective member 50 is generally a strain relief boot
and is positioned so as to completely enclose the interface between
the conductor 30 and the housing 22. The protective member is
effective to protect the areas which it encloses from damage and
short circuits that could be caused by, for example, body fluids.
The protective member 50 should be made of a biocompatible
material. Preferably, the protective member is made out of a
biocompatible, insulating material such as silicone or
polyurethane.
[0031] The protective member may be shaped and positioned in
several ways, two of which are shown in FIGS. 5A and 5B. In each
instance, however, the protective member should enclose the
interface between the conductor 30 to the housing 22. In FIGS. 1, 5
and 6, an exemplary interface between the conductor 30 and the
housing 22 is provided as a crimp connection 34. The protective
member 50 of FIG. 5A and of FIG. 5B can be connected to the housing
22 using medical grade adhesive. Preferably, the medical grade
adhesive is applied onto the entire outer perimeter of the
protective member 50 and is also used to fill the entire area
enclosed within the protective member.
[0032] The protective member 50 may be positioned a number of ways
with respect to the housing 22. Factors which influence the
positioning of the protective member with respect to the housing
include, but are not limited to, the location and depth of the
tissue site at which the device 10' is implanted.
[0033] The protective member 50 should be connected to the housing
22 via an appropriate adhesive. The adhesive should be effective to
ensure the integrity of the connection between the protective
member 50 and the housing 22 while the device 10' is implanted. The
adhesive may also be used as a potting material to fill any gaps or
pockets within the protective member 50. Acceptable adhesive
materials will be known to the skilled artisan, however, one
particular example is a medial grade adhesive.
[0034] FIGS. 5A, 5B and 6 also show a securing mechanism 60 which
is effective to ensure that the device 10' remains secured to
particular tissue site. One exemplary securing mechanism 60, as
best shown in FIG. 6, is a tie-down mechanism, which allows for the
housing 22 of the device 10' to be connected, for example by
suturing, to a tissue site 61. The exemplary tie-down mechanism
includes three lobes 62 which lie approximately 120.degree. apart
from each other, wherein each lobe generally has at least one
suture site 64. One of ordinary skill in the art will realize that
the number of lobes 62, and/or the number of suture sites 64 may be
greater or lesser than the numbers that are described above and/or
that are depicted in FIG. 6, and that each lobe 62 may be separated
from the other lobes by an angle measurement greater or less than
120.degree..
[0035] As shown in exemplary FIG. 6, the suture sites 64 should be
sized and placed in order to allow for one end of a suture thread
65 to be connected to the tissue site 61 through the securing
mechanism 60 at each lobe 62. One of ordinary skill in the art will
realize that each lobe 62 can have greater or less than one suture
site 64, and a suture thread 65 does not necessarily have to be
connected to the tissue site 61 at each suture site 64.
[0036] Those skilled in the art will recognize, or be able to
ascertain using no more than routine experimentation, numerous
equivalents to the specific procedures described herein. Such
equivalents are considered to be within the scope of this invention
and are covered by the following claims.
[0037] The contents of all references and patent applications
described herein are hereby incorporated by reference.
* * * * *