U.S. patent application number 14/100918 was filed with the patent office on 2014-06-12 for implantable actuator for hearing aid application.
The applicant listed for this patent is Hans BERNHARD, Karen CAUWELS, Joel FONTANNAZ, Markus HALLER, Rudolph HAUSLER, Karel HUYBRECHTS, Thomas KAISER, Ben KLOECK, Christian PECLAT, Christof STIEGER. Invention is credited to Hans BERNHARD, Karen CAUWELS, Joel FONTANNAZ, Markus HALLER, Rudolph HAUSLER, Karel HUYBRECHTS, Thomas KAISER, Ben KLOECK, Christian PECLAT, Christof STIEGER.
Application Number | 20140163309 14/100918 |
Document ID | / |
Family ID | 36564670 |
Filed Date | 2014-06-12 |
United States Patent
Application |
20140163309 |
Kind Code |
A1 |
BERNHARD; Hans ; et
al. |
June 12, 2014 |
IMPLANTABLE ACTUATOR FOR HEARING AID APPLICATION
Abstract
An electromechanical actuator for an implantable hearing aid
device including a mechanical output structure that has a first
portion and a second portion, wherein the first portion is a
mechanical attachment structure to attach a stapes prosthesis, and
wherein the second portion is a wire-like member coupling the
mechanical attachment structure to a magnetically permeable
armature shaft assembly.
Inventors: |
BERNHARD; Hans; (Koniz,
CH) ; FONTANNAZ; Joel; (Bulle, CH) ; PECLAT;
Christian; (Neuchatel, CH) ; HALLER; Markus;
(Yens, CH) ; CAUWELS; Karen; (Kessel-Lo, BE)
; KLOECK; Ben; (Edegem, BE) ; HUYBRECHTS;
Karel; (Kapeele op den Bos, BE) ; STIEGER;
Christof; (Bern, CH) ; HAUSLER; Rudolph;
(Celigny, CH) ; KAISER; Thomas; (Borgerhoot,
BE) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
BERNHARD; Hans
FONTANNAZ; Joel
PECLAT; Christian
HALLER; Markus
CAUWELS; Karen
KLOECK; Ben
HUYBRECHTS; Karel
STIEGER; Christof
HAUSLER; Rudolph
KAISER; Thomas |
Koniz
Bulle
Neuchatel
Yens
Kessel-Lo
Edegem
Kapeele op den Bos
Bern
Celigny
Borgerhoot |
|
CH
CH
CH
CH
BE
BE
BE
CH
CH
BE |
|
|
Family ID: |
36564670 |
Appl. No.: |
14/100918 |
Filed: |
December 9, 2013 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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11719975 |
Mar 25, 2008 |
8602964 |
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14100918 |
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PCT/AU2005/001801 |
Nov 30, 2005 |
|
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11719975 |
|
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60631512 |
Nov 30, 2004 |
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Current U.S.
Class: |
600/25 |
Current CPC
Class: |
H04R 25/606 20130101;
H04R 2225/61 20130101; H04R 25/60 20130101; A61F 2/18 20130101;
H04R 2225/41 20130101; A61F 2002/183 20130101 |
Class at
Publication: |
600/25 |
International
Class: |
H04R 25/00 20060101
H04R025/00 |
Claims
1.-33. (canceled)
34. An electromechanical actuator for an implantable hearing aid
device comprising: a hermetic housing of tubular shape closed on
one side with a diaphragm and on the other side, with a hermetic
feedthrough; first and second magnets located in said hermetic
housing arranged to provide a biasing field in a field region
between two substantially opposed pole faces of said first and
second magnets; a magnetically permeable armature located in said
biased field region between said opposed pole faces, the location
of the magnetically permeable armature defining a first and second
working gap between the magnetically permeable armature and
respective opposed pole faces of the first and second magnets; a
magnetically permeable armature shaft assembly supporting said
magnetically permeable armature, said magnetically permeable
armature shaft assembly arranged to allow movement of said
magnetically permeable armature between said opposed pole faces in
a longitudinal direction defined by the movement of said
magnetically permeable armature shaft assembly; biasing means to
provide a biasing force to said magnetically permeable armature
shaft assembly to bias said magnetically permeable armature to a
predetermined location between said opposed pole faces; magnetic
flux generating means including an electrical signal coil
responsive to an input signal delivered by an electrical connection
to said hermetic feedthrough to generate a signal flux to modulate
the biasing field in said field region thereby providing an
unbalanced force to said magnetically permeable armature causing
actuation of said magnetically permeable armature shaft assembly; a
mechanical output structure including stimulation means to
stimulate the inner ear auditory system responsive to actuation of
said magnetically permeable armature shaft assembly; and a lead
electrically connected to outer pins of said hermetic feedthrough
and mechanically attached to said titanium housing, wherein said
mechanical output structure has a first portion and a second
portion, and wherein the first portion is a mechanical attachment
structure to attach a stapes prosthesis, and wherein said second
portion is a wire-like member coupling said mechanical attachment
structure to said magnetically permeable armature shaft
assembly.
35. An electromechanical actuator for an implantable hearing aid
device as claimed in claim 34, wherein said mechanical attachment
structure is of substantially cylindrical shape with an elliptical
cross section having a numeric eccentricity ranging from
approximately 0 to approximately 0.5.
36. An electromechanical actuator for an implantable hearing aid
device as claimed in claim 34, wherein said mechanical attachment
structure is covered with a silicone layer having a thickness of
approximately 0.05 mm to approximately 0.2 mm
37. An electromechanical actuator for an implantable hearing aid
device as claimed in claim 34, wherein said wire-like member is a
straight rod, and further wherein an angle between said mechanical
attachment structure and said straight rod is chosen in the range
of approximately 80.degree. to approximately 150.degree..
38. An electromechanical actuator for an implantable hearing aid
device as claimed in claim 37, wherein said angle between said
mechanical attachment structure and said straight rod is in the
range from approximately 115.degree. to approximately
125.degree..
39. An electromechanical actuator for an implantable hearing aid
device as claimed in claim 37, wherein ball joint means is disposed
between said mechanical attachment structure and said straight rod
to allow reorientation of said mechanical attachment structure with
respect to said straight rod.
40. An electromechanical actuator for an implantable hearing aid
device as claimed in claim 34, wherein said wire-like member is at
least partially bendable during implantation of said implantable
hearing aid device.
41. An electromechanical actuator for an implantable hearing aid
device as claimed in claim 34, wherein said mechanical attachment
structure includes further ball joint means to engage with a stapes
prosthesis provided with a ball-shaped head.
Description
RELATED APPLICATIONS
[0001] The present application is related to U.S. Provisional
Patent Application No. 60/631,512 entitled "Implantable Fixation
System for Anchorage of Medical Devices," filed 30 Nov. 2004, which
is hereby incorporated by reference herein in its entirety.
FIELD OF THE INVENTION
[0002] The present invention relates to treatments for hearing
loss. In a particular form, the present invention relates to an
implantable actuator capable of direct stimulation of the middle
and inner ear auditory systems.
BACKGROUND OF THE INVENTION
[0003] Today state-of-the-art conventional hearing aids are able to
treat hearing loss, in particular sensorineural hearing loss, very
efficiently but still have some major disadvantages such as
occlusion of the auditory canal, feedback at high amplification
levels and stigmatization of the patients with hearing loss.
Further they are rather ineffective in the treatment of conductive
and mixed hearing loss. Whilst the present invention is described
in relation to the treatment of hearing loss it will be appreciated
that the invention will have other applications consistent with the
principles described in the specification.
[0004] It is an object of the present invention to provide a
stimulation device capable of being included in an implantable
hearing aid device that addresses one or more of the disadvantages
of conventional hearing aid devices.
SUMMARY OF THE INVENTION
[0005] In a first aspect the present invention accordingly provides
an electromechanical actuator comprising: [0006] first and second
magnets arranged to provide a biasing field in a field region
between two substantially opposed pole faces of said first and
second magnets; [0007] a magnetically permeable armature located in
said biased field region between said opposed pole faces, the
location of the magnetically permeable armature defining a first
and second working gap between the magnetically permeable armature
and respective opposed pole faces of the first and second magnets;
[0008] a magnetically permeable armature shaft assembly supporting
said magnetically permeable armature, said magnetically permeable
armature shaft assembly arranged to allow movement of said
magnetically permeable armature between said opposed pole faces in
a longitudinal direction defined by the movement of said armature
shaft assembly; [0009] biasing means for providing a biasing force
to said magnetically permeable armature shaft assembly to bias said
magnetically permeable armature to a predetermined location between
said opposed pole faces; and [0010] magnetic flux generating means
responsive to an input signal to generate a signal flux to modulate
said biasing field in said field region thereby providing an
unbalanced force to said magnetically permeable armature causing
actuation of said magnetically permeable armature shaft
assembly.
[0011] Preferably, said first and second magnets are supported by a
magnet support assembly and wherein said magnet support assembly,
said magnetically permeable armature and said first and second
working gaps form a first magnetic circuit.
[0012] Preferably, said magnetic flux generating means is supported
by a flux generating means support assembly and wherein said flux
generating means support assembly, said magnetically permeable
armature, said magnetically permeable armature shaft assembly and
one of said first and second working gaps forms a second magnetic
circuit.
[0013] Preferably, said magnetic flux generating means comprises an
electrical coil.
[0014] Preferably, said flux generating means support assembly
comprises a magnetically permeable structure having a recess to
receive a shaft of said magnetically permeable armature shaft
assembly, thereby forming a transverse air gap between said shaft
and the walls of said recess.
[0015] Preferably, said recess is substantially cylindrical in
shape.
[0016] Preferably, said transverse air gap is minimized to reduce
the reluctance of said second magnetic circuit.
[0017] Preferably, said biasing means includes a first biasing
member and a second biasing member.
[0018] Preferably, said flux generating means support assembly
comprises said first biasing member and wherein said first biasing
member further comprises a magnetically permeable spring in
mechanical contact with a shaft of said magnetically permeable
armature shaft assembly.
[0019] Preferably, said second biasing member comprises a diaphragm
in mechanical contact with said shaft.
[0020] In a second aspect the present invention accordingly
provides an electromechanical actuator for an implantable hearing
aid device comprising: [0021] a hermetic housing of tubular shape
closed on one side with a diaphragm and on the other side, with a
hermetic feedthrough; [0022] first and second magnets located in
said hermetic housing arranged to provide a biasing field in a
field region between two substantially opposed pole faces of said
first and second magnets; [0023] a magnetically permeable armature
located in said biased field region between said opposed pole
faces, the location of the magnetically permeable armature defining
a first and second working gap between the magnetically permeable
armature and respective opposed pole faces of the first and second
magnets; [0024] a magnetically permeable armature shaft assembly
supporting said magnetically permeable armature, said magnetically
permeable armature shaft assembly arranged to allow movement of
said magnetically permeable armature between said opposed pole
faces in a longitudinal direction defined by the movement of said
magnetically permeable armature shaft assembly; [0025] biasing
means to provide a biasing force to said magnetically permeable
armature shaft assembly to bias said magnetically permeable
armature to a predetermined location between said opposed pole
faces; [0026] magnetic flux generating means including an
electrical signal coil responsive to an input signal delivered by
an electrical connection to said hermetic feedthrough to generate a
signal flux to modulate the biasing field in said field region
thereby providing an unbalanced force to said magnetically
permeable armature causing actuation of said magnetically permeable
armature shaft assembly; [0027] a mechanical output structure
including stimulation means to stimulate the inner ear auditory
system responsive to actuation of said magnetically permeable
armature shaft assembly; and [0028] a lead electrically connected
to outer pins of said hermetic feedthrough and mechanically
attached to said titanium housing.
[0029] In a third aspect the present invention accordingly provides
an implantable stimulation device for stimulating an inner ear of a
patient, said stimulation device including an electromechanical
actuator responsive to an auditory signal for providing mechanical
stimulation to said inner ear in response to said auditory
signal.
[0030] Preferably, said stimulation device further includes a
middle ear prosthetic, said middle ear prosthetic reproducing in
part or in full the function of the middle ear, wherein said
electromechanical actuator includes actuation means to actuate said
middle ear prosthetic thereby stimulating said inner ear in
response to said auditory signal.
BRIEF DESCRIPTION OF THE DRAWINGS
[0031] A preferred embodiment of the present invention will be
discussed with reference to the accompanying drawings wherein:
[0032] FIG. 1 is a perspective view of the interior components of
an implantable hearing aid device incorporating an
electromechanical actuator in accordance with a first embodiment of
the present invention;
[0033] FIG. 2 is a composite view of the implantable hearing aid
device illustrated in FIG. 1;
[0034] FIG. 3 is an elevation view in longitudinal diametric
section of the electromechanical actuator illustrated in FIG. 1
having a low reluctance transverse gap;
[0035] FIG. 4 is an elevation view in longitudinal diametric
section of a second embodiment of an electromechanical actuator of
the present invention having a flux conducting spring member;
[0036] FIG. 5 is a lower elevation view in longitudinal diametric
section of the electromechanical actuator illustrated in FIG. 1,
showing the attachment of coil wires and lead;
[0037] FIG. 6 is an elevation view in longitudinal diametric
section of the electromechanical actuator illustrated in FIG. 1,
showing the mechanical output structure;
[0038] FIG. 7 is a side view of the mechanical output structure
illustrated in the above figures, with an attached stapes
prosthesis;
[0039] FIG. 8 is a side view of the mechanical output structure
illustrated in the above figures, having a ball joint between
coupling rod and artificial incus;
[0040] FIG. 9 is a side view of the mechanical output structure
illustrated in the above figures, having a bendable coupling
rod;
[0041] FIG. 10 is a side view of the mechanical output structure
illustrated in the above figures, having a partially bendable
coupling rod;
[0042] FIG. 11 is a side view of the mechanical output structure
illustrated in the above figures, having a ball joint between
artificial incus and stapes prosthesis; and
[0043] FIG. 12 is a perspective view of a cochlear implant system
showing one exemplary application of the electromechanical actuator
of the present invention.
[0044] In the following description, like reference characters
designate like or corresponding parts throughout the several views
of the drawings.
DESCRIPTION OF PREFERRED EMBODIMENT
[0045] Referring now to FIGS. 1 and 2, there are shown perspective
and composite views depicting the components of an implantable
hearing aid device 100 incorporating an electromechanical actuator
50 according to a first embodiment of the present invention.
Hearing aid device 100 includes a housing 1 formed from titanium
tubing that is substantially cylindrical and of circular cross
section. Hearing aid device 100 further comprises a titanium
diaphragm 6, a titanium ring 21 and a multi-pin feedthrough 9 which
are joined by hermetic laser welds. Coupling rod 7, which is part
of the moving mechanical output structure of electromechanical
actuator 50, is placed in ring 21 and is hermetically welded to it.
This assembly provides a hermetically closed housing 1 that is
suitable for implantation in the human body.
[0046] Lead 11 which provides the input signal to electromechanical
actuator 50 is connected to feedthrough 9. To protect the
connection site of the lead 11, electromechanical actuator 50 may
be covered by a silicone filled titanium cap 10. In this embodiment
directed to a hearing aid device, the titanium cap 10 provides
multiple flat surface regions to allow secure manipulation of the
device during implantation with surgical tweezers or little tongs.
The titanium cap 10 also has a conical shape that provides
mechanical transition between the small diameter of the lead 11 and
larger diameter of the titanium tube 1.
[0047] Referring now to FIG. 3, there is shown an elevation view in
longitudinal diametric section of the first embodiment of
electromechanical actuator 50 of the present invention
incorporating a low reluctance transverse gap. Armature 2, shaft 12
and coupling rod 7 form the moving part of the actuator 50. As
armature 2 and shaft 12 form part of the magnetic circuits which
drive electromechanical actuator 50 they are made of soft magnetic
alloys. However, as would be understood by those skilled in the
art, other suitable materials having the desired magnetic
permeability properties may also be used.
[0048] Shaft 12 is made of titanium to enable hermetic closing of
the actuator by welding it to a ring 21. The resulting moving
structure is elastically supported at one side by a diaphragm 6,
which performs the function of a restoring spring. As such,
diaphragm 6 prevents magnetic snap over. On the other side, shaft
12 is supported in the longitudinal direction by a spring bearing 5
having a spring constant sufficient to provoke, together with
diaphragm 6, the demanded dynamic characteristic of this
spring-mass structure.
[0049] The armature 2 is centred between two permanent magnets 3a
and 3b thereby forming two working gaps 17a and 17b. Both magnets
3a and 3b are polarized in the same direction substantially in
parallel to the actuator axis and the direction of movement of
shaft 12, and provide polarizing flux in working gaps 17a and 17b
that extends through the armature 2. This first magnetic circuit is
closed through the magnet supports 16a and 16b and the short sleeve
15 which are again fabricated from soft magnetic alloys.
[0050] A second magnetic circuit comprises signal coil 4, coil core
13, long sleeve 14, the magnet support 16b, the armature 2 and the
shaft 12. Signal coil 4 includes two input coil wires 23 which are
connected to lead 11 by virtue of feedthrough 9. Preferably, all
elements forming the second magnetic circuit other than the signal
coil 4 are made of soft magnetic alloys to conduct the signal flux
generated by coil 4. This magnetic signal circuit includes two air
gaps: the working gap 17b and a transverse gap 18 formed between
the coil core 13 and the shaft 12. The transverse gap 18 between
the coil core 13 and shaft 12 has been minimized in order to
provide a low reluctance thereby minimize losses in the magnetic
circuit.
[0051] In operation, the signal flux passing through the working
gap 17b has the effect of modulating the polarizing flux generated
by the magnets 3a and 3b in the process either increasing or
decreasing the flux in the working gap 17b depending on the
direction of the current passing through the signal coil 4. This in
turn increases or decreases the attractive force in gap 17b
compared to the constant polarizing flux in gap 17a which results
in a net force pulling the armature upwards or downwards. In this
manner, small changes in the signal flux generated by coil 4 will
result in corresponding actuation of shaft 12 thereby providing an
electromechanical actuator of enhanced sensitivity.
[0052] Referring now to FIG. 4, there is shown an elevation view in
longitudinal diametric section of a second embodiment of an
electromechanical actuator 55. The main structure of the
electromechanical actuator 55 is the same as shown in FIG. 3,
however, the spring bearing 5 and the transverse gap 18 of the FIG.
3 embodiment are replaced by flux conducting spring members 25 in
this second embodiment. Flux conducting spring members 25 are
preferably made of soft magnetic alloys providing reduced
reluctance to overcome the losses resulting from the increased air
gap 18 when compared to the air gap between the shaft 12 and coil
core 13 in the first embodiment.
[0053] The use of multiple spring members 25 separated by flux
conducting spacers 26 increases the sectional area that can be
passed by the magnetic flux to further reduce the overall
reluctance of the magnetic circuit. Compared to one spring that is
simply increased in thickness, the multiple springs provide higher
compliance.
[0054] Referring now to FIG. 5, there is shown an elevation view in
longitudinal diametric section of the first embodiment of the
electromechanical actuator 55 showing the attachment of the coil
wires 23 and lead 11. Coil wires 23 are attached to feedthrough
pins 24 by, for example, brazing, welding or gluing with an
electrically conductive glue. To prevent coil wires 23 from coming
into contact with moving shaft 12 or spring bearing 5, a cover 20
is placed between the coil wires and the shaft.
[0055] The terminals 27 of lead 11 are inserted in a crimping tube
31 that is welded to the feedthrough pin 24. Crimping the tube 31
mechanically attaches lead terminal 27 and establishes a
low-impedance electrical connection. In this embodiment, a cap 10
protects the whole connection site. The cavity 32 formed by the cap
10 is filled up with silicone to provide a firm mechanical
attachment of the lead 11. To enable proper sterilization of the
silicone, the cap 10 provides multiple openings 28.
[0056] Referring now to FIG. 6, there is shown an elevation view in
longitudinal diametric section of the moving mechanical output
structure 110 forming part of the implantable hearing aid device
100 illustrated in FIGS. 1 and 2. Mechanical output structure 110
comprises a coupling rod 7 and an artificial incus 8, both made of
titanium and, in this embodiment, welded together. A silicone
coating 38 covers artificial incus 8. The artificial incus 8
closely emulates the long process of the incus of the human middle
ear, and is placed next to it during implantation.
[0057] The length of the coupling rod 7, measured from the outer
surface of the diaphragm 6 to the end of the coupling rod 7, is
chosen in the range from approximately 3 mm to approximately 20 mm,
and preferably in the range from approximately 5 mm to
approximately 8 mm, to place the artificial incus 8 in the intended
location. The angle formed by the axis of the coupling rod 7 and
the axis of the artificial incus 8 is chosen in the range from
80.degree. to 150.degree., preferably in the range from 115.degree.
to 125.degree., in order to correctly orientate the artificial
incus 8 according to the anatomical conditions in the human middle
ear.
[0058] The cross sectional profile of the artificial incus 8 is
elliptical with a numeric eccentricity in the range from 0 to 0.5
in order to provide reliable mechanical connection of the stapes
prosthesis by crimping. Additionally, the artificial incus 8 is
covered with a silicone coating 38 that has a thickness chosen in
the range from 0.05 mm to 0.2 mm in order to allow proper stapes
prosthesis attachment and crimping. It should be appreciated that
the above dimensions and distances are approximate and that other
dimensions may be established in alternative embodiments.
[0059] Referring now to FIG. 7, there is shown a schematic diagram
of one embodiment of the mechanical output structure of FIG. 6 with
an attached stapes prosthesis 33.
[0060] Referring now to FIG. 8, there is shown another embodiment
of the mechanical output structure having a ball joint 35 between
coupling rod 39 and artificial incus 40 to allow intra-operative
adjustment of the angle between the coupling rod 39 and the
artificial incus 40.
[0061] Referring now to FIG. 9, there is shown yet another
embodiment of the mechanical output structure having a bendable
coupling rod 41 to allow intra-operative adjustment of the
orientation and the location of the artificial incus 8. FIG. 10
shows yet another embodiment of the mechanical output structure
having a two part coupling rod, a stiff part 42 next to actuator
50, 55 and a bendable part 36 next to the artificial incus 8 to
allow intra-operative adjustment of the orientation and the
location of the artificial incus 8.
[0062] Referring now to FIG. 11, there is shown a further
embodiment of the mechanical output structure having a stapes
prosthesis 34 directly attached to the artificial incus 43 via a
ball joint 37 to allow intra-operative adjustment of the insertion
angle of the stapes prosthesis 34.
[0063] Referring now to FIG. 12, there is shown implantable hearing
aid device 1200 implementing an electromechanical actuator 1210
according to a preferred embodiment of the present invention. In
this preferred embodiment, implantable hearing aid device 1200 is a
totally implantable Cochlear.TM. prosthesis (also referred to as a
Cochlear.TM. implant system, Cochlear.TM. prosthetic device and the
like) which functions as an implantable stimulation device for
stimulating the inner ear by employing an electromechanical
actuator responsive to an auditory signal. As would be apparent to
those skilled in the art, the electromechanical actuator of the
present invention can be utilized in current or future implantable
medical devices. These implantable medical devices can be either
partially or totally implanted in an individual, and such
implantation may be temporary or permanent.
[0064] Hearing aid device 1200 comprises external component
assembly 1242 which is directly or indirectly attached to the body
of the recipient, and an internal component assembly 1244 which is
temporarily or permanently implanted in the recipient. External
assembly 1242 typically comprises audio pickup devices 1220 for
detecting sound, a speech processing unit 1216, a power source (not
shown), and an external transmitter unit 1206 comprising an
external coil 1208. Speech processing unit 1216 processes the
output of audio pickup devices 1220 that are positioned by the ear
1222 of the recipient. Speech processing unit 1216 generates coded
signals which are provided to external transmitter unit 1206 via
cable 1218.
[0065] Internal components 1244 comprise an internal receiver unit
1212, a stimulator unit 1226, and a moving electromechanical
actuator 1210 according to a preferred embodiment of the present
invention. Internal receiver unit 1212, which comprises an internal
transcutaneous transfer coil 1224, and stimulator unit 1226 are
hermetically sealed within a housing 1228. Collectively,
transmitter antenna coil 1208 and receiver antenna coil 1224 form
an inductively-coupled coil system used to transfer data and power
via a radio frequency (RF) link 114. A cable 1230 extends from
stimulator unit 1226 to actuator 1210.
[0066] Actuator 1210 is coupled to the inner ear fluids via
artificial incus 8 extending through a cochleostomy. Signals
generated by stimulator unit 1226 are applied by mechanical
actuator 1210 to inner ear fluids. It should be appreciated that
the arrangement shown in FIG. 12 is a schematic representation
only, and that embodiments of the electromechanical actuator 1210
of the present invention may be positioned in a variety of
locations to provide the desired stimulative effect. For example,
in the embodiment shown in FIG. 12, actuator 1210 is coupled to the
inner ear fluids via artificial incus 8. However, a variety of
stapes prostheses may be attached to artificial incus 8 in
alternative embodiments, as described above.
[0067] It should also be appreciated that electromechanical
actuator 1210 may be secured to the recipient utilizing a variety
of techniques now or later developed. In one embodiment,
electromechanical actuator 1210 is configured to be implanted in a
recipient utilizing an embodiment of a fixation system described in
commonly owned U.S. Provisional Patent Application No. 60/631,512
entitled "Implantable Fixation System for Anchorage of Medical
Devices," filed 30 Nov. 2004, which is hereby incorporated by
reference herein in its entirety.
[0068] A brief consideration of the above described embodiments
will indicate that the invention may be employed to remedy any
source of conductive hearing loss. Additionally, these embodiments
of the electromechanical actuator may be configured to provide
sufficiently high output levels to treat severe sensorineural
hearing loss while being sufficiently small to completely fit into
a human mastoid.
[0069] It should also be appreciated that Cochlear.TM. implant
system 1200 described above is just one exemplary system in which
the electromechanical actuator of the present invention may be
implemented. The electromechanical actuator of the present
invention may be implemented in a myriad of embodiments of a
cochlear implant system, hearing aid or other medical devices or
systems now or later developed.
[0070] Advantageously, the dimensions and shape of embodiments of
the electromechanical actuator of the present invention may be
selected to take into account the anatomy of the implantation site.
For example, for an actuator that is to be placed in a hole drilled
into the human mastoid, an elongated cylindrical shape such as that
described above has been found to be advantageous. In addition, in
the above or other application, embodiments of the actuator may
have a diameter and a length which are sufficiently small to allow
placement of the actuator in narrow anatomical locations as
required. A further advantage of embodiments of the present
invention directed to hearing aid devices is that they are able to
deliver sufficiently high output levels to manage progressive
hearing loss in order to prevent revision surgeries. A still
further advantage is that certain embodiments of the actuator are
highly energy efficient thereby minimizing power consumption and
facilitating autonomy.
[0071] Although a preferred embodiment of the method and system of
the present invention has been described in the foregoing detailed
description, it will be understood that the invention is not
limited to the embodiment disclosed, but is capable of numerous
rearrangements, modifications and substitutions without departing
from the scope of the invention as set forth and defined by the
following claims.
[0072] It will be understood that the term "comprise" and any of
its derivatives (eg. comprises, comprising) as used in this
specification is to be taken to be inclusive of features to which
it refers, and is not meant to exclude the presence of any
additional features unless otherwise stated or implied.
* * * * *