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Patent 2209068 Summary

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Claims and Abstract availability

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(12) Patent: (11) CA 2209068
(54) English Title: ARTICULATED HEARING DEVICE
(54) French Title: DISPOSITIF DE CORRECTION AUDITIVE ARTICULE
Status: Deemed expired
Bibliographic Data
(51) International Patent Classification (IPC):
  • H04R 25/02 (2006.01)
(72) Inventors :
  • SHENNIB, ADNAN (United States of America)
  • URSO, RICHARD (United States of America)
(73) Owners :
  • DECIBEL INSTRUMENTS, INC. (United States of America)
(71) Applicants :
  • DECIBEL INSTRUMENTS, INC. (United States of America)
(74) Agent: SMITH, PAUL RAYMOND
(74) Associate agent: OYEN WIGGS GREEN & MUTALA LLP
(45) Issued: 1999-07-06
(86) PCT Filing Date: 1995-12-27
(87) Open to Public Inspection: 1996-07-11
Examination requested: 1997-12-12
Availability of licence: N/A
(25) Language of filing: English

Patent Cooperation Treaty (PCT): Yes
(86) PCT Filing Number: PCT/US1995/017113
(87) International Publication Number: WO1996/021334
(85) National Entry: 1997-06-27

(30) Application Priority Data:
Application No. Country/Territory Date
08/365,913 United States of America 1994-12-29

Abstracts

English Abstract




A hearing device (10) having highly articulated, non-contiguous parts and
adapted for placement within the ear canal (20) includes a receiver module
(40) for delivering acoustic signals within close proximity to the tympanic
membrane (26), a main module (12) containing all hearing aid components except
the receiver, and a connector (50) that routes amplified electrical signals
from the main module (12) to the receiver module (40). The connector (50) fits
in the cartilaginous area (28) of the ear canal (20) and is articulated with
both the receiver module (40) and main module (12) to permit independent
movement of the receiver module (40) while the hearing device (10) is inserted
or removed and during various jaw movements, such as chewing, yawning and
talking.


French Abstract

Dispositif de correction auditive (10) muni de parties hautement articulées, non contiguës et prévu pour être placé à l'intérieur du conduit auditif (20), comportant un module récepteur (40) pour transmettre des signaux acoustiques à proximité de la membrane tympanique (26), un module principal (12) contenant tous les éléments de la prothèse auditive sauf le récepteur, et un connecteur (50) qui achemine les signaux électriques amplifiés du module principal (12) au module récepteur (40). Le connecteur (50) s'insère dans la zone cartilagineuse (28) du conduit auditif (20) et est articulé avec le module récepteur (40) et le module principal (12) pour permettre au module récepteur (40) de se déplacer de manière indépendante pendant l'insertion ou le retrait du dispositif de correction auditive (10) ainsi qu'au cours de divers mouvements de la mâchoire tels que mastication, bâillement ou parole.

Claims

Note: Claims are shown in the official language in which they were submitted.



CLAIMS

1. A hearing device, comprising:
a main module adapted to contain any of a microphone, a battery, device
controls, and a signal processing circuit;
a receiver module adapted to contain a receiver; and
a connector adapted to provide an electrical connection between said main
module and said receiver module;
wherein at least two of said main module, receiver module, and connector
are connected by an articulating joint, such that said modules move freely and
independently, one relative to the other within a range of movement and to
freely maintain a position at any point within this range of movement to permit
independent movement of any of said main module and said receiver module in
response to in situ ear canal deformation; and wherein said main module and
said receiver module are each contained in separate, relatively rigid,
non-resilient housings.

2. The hearing device of Claim 1, wherein said main module is
positioned in a medial concha area of said ear canal just behind the tragus.

3. The hearing device of Claim 1, said main module further comprising:
a face-plate positioned either flush with or beyond an ear canal aperture.

4. The hearing device of Claim 1, further comprising a face-plate,
wherein said controls are trimmers mounted on said face-plate.

5. The hearing device of Claim 1, where main module controls are
programmed into said main module.
23

6. The hearing device Claim 1, said connector further comprising:
a covering for reducing oscillatory feedback.

7. The hearing device of Claim 1, said connector further comprising:
a covering having an absorbent layer for cerumen collection.

8. The hearing device of Claim 1, said receiver module further
.
comprising:
an acoustic seal.

9. The hearing device of Claim 8, said acoustic seal further comprising:
a soft and compliant material.

10. The hearing device of Claim 8, said acoustic seal further comprising:
a soft and compliant bulbous ending.

11. The hearing device of Claim 8, wherein said acoustic seal is made of
any of a silicone material or a foam material.

12. The hearing device of Claim 8, wherein said acoustic seal is either
disposable, washable, or both.

13. The hearing device of Claim 8, said acoustic seal further comprising:
a snap-on seal tip.

14. The hearing device of Claim 8, said acoustic seal further comprising:
a threaded seal tip.

15. The hearing device of Claim 8, said acoustic seal further comprising:
a tip that is articulated with respect to said receiver module.


24


16. The hearing device of Claim 8, said acoustic seal further comprising:
at least one sealing ring.

17. The hearing device of Claim 8, said acoustic seal further comprising:
a removable sleeve.

18. The hearing device of Claim 8, wherein any or all of said main
module, said receiver module, said connector and said acoustic seal are
provided in assorted, standard sizes.

19. The hearing device of Claim 8, wherein any or all of said main
module, said receiver module, said connector and said acoustic seal are custom
manufactured.

20. The hearing device of Claim 1, wherein said articulation is achieved
by at least one of:
a single point of articulation between said main module and said receiver
module;
a single point of articulation between said receiver module and said
connector;
a dual point of articulation at each end of said connector; and
a flexible connector adapted to provide at least one point of articulation
between said receiver module and said main module.

21. The hearing device of Claim 1, further comprising:
means adapted to provide said articulation.



22. The hearing device of Claim 1, wherein said receiver module is
adapted to be positioned in any one of:
the bony area of the ear canal; and
the deeper cartilaginous area of the ear canal.

23. The hearing device of Claim 1, wherein the diameter of either of said
connector, said articulating joint, or said receiver module is less than the
diameter of the individual's ear canal.

24. The hearing device of Claim 1, wherein said connector is adapted to
be positioned in the cartilaginous area of the ear canal.

25. The hearing device of Claim 1, wherein said connector is adjustable
to accommodate a variety of individual ear canal lengths, and to permit receiverplacement at a selected depth in the ear canal.

26. The hearing device of Claim 1, further comprising:
means for adjusting the length of said connector length, said adjusting
means comprising at least one of:
a turnbuckle shaft; and
a telescoping shaft.

27. The hearing device of Claim 1, further comprising:
a plurality of modular, differently dimentioned, detachable sizers, said
sizers being adapted to determine at least optimal hearing device size, patient
comfort, hearing device ear canal insertion depth tolerance, ease of ear canal
insertion and removal, appearance, and overall hearing device physical
characteristics .

26


28. The hearing device of Claim 1, said main module further
comprising:
a vent adapted to receive a probe tube.

29. The hearing device of Claim 1, said main module further
comprising:
at least one vent adapted to vent the patient's ear canal to thereby reduce
occlusion effect and improve air circulation.

30. The hearing device of Claim 1, said receiver module further
comprising:
a canal adapted to receive a probe tube.

31. The hearing device of Claim 1, said receiver module further
comprising:
a canal adapted to provide pressure relief.

32. The hearing device of Claim 1, said main module including a
microphone, wherein said microphone is adapted to receive direct acoustic
input from a receiver in accordance with virtual electroacoustic audiometry.

33. The hearing device of Claim 1, wherein said receiver module is
adapted for deep insertion into the patient's ear canal to minimize or eliminateocclusion effects.

34. The hearing device of Claim 1, said connector further comprising:
means for reducing vibration-caused oscillatory feedback.

35. The hearing device of Claim 34, wherein said means for reducing
vibration-caused oscillatory feedback are made of a viscoelastic material.


27


36. The hearing device of Claim 1, said connector further comprising:
means for reducing piston action caused oscillatory feedback.

37. The hearing device of Claim 36, wherein said means for reducing
piston action caused oscillatory feedback are made of a viscoelastic material.

38. An intra-canal prosthesis (ICP) that is representative of a hearing aid
prostheses, said ICP being adapted to perform unaided, simulated aided hearing
evaluation in accordance with virtual electroacoustic audiometry, said ICP
comprising:
a main module adapted to provide an electrical connection to a virtual
electroacoustic audiometer;
a receiver module adapted to contain a receiver, and
a connector adapted to provide an electrical connection between said main
module and said receiver module;
wherein at least two of said main module, receiver module, and connector
are connected by an articulating joint, such that said modules move freely and
independently, one relative to the other within a range of movement and to
freely maintain a position at any point within this range of movement, to permitindependent movement of any of said main module, said receiver module, and
said connector in response to in situ ear canal deformation; and wherein said
main module and said receiver module are each contained in separate,
relatively rigid, non-resilient housings.

39. The hearing device of Claim 1, wherein said receiver module and
said main module are acoustically and/or vibrationally isolated from each other.
28


40. The hearing device of Claim 1, further comprising:
an acoustic seal that is adapted to be positioned in any one of:
the bony area of the ear canal; or
the deeper cartilaginous area of the ear canal.

41. The hearing device of Claim 8, wherein said acoustic seal is coupled
to said receiver to seal said ear canal and thereby prevent oscillatory feedback.

42. The hearing device of Claim 1, wherein said main module and said
receiver module are contained in, or associated with, separate, non-contiguous
housings.

43. The hearing device of Claim 21, wherein said articulation means
comprise any of:
a ball joint;
a flexible joint; and
a tapered boot.

44. The hearing device of Claim 21, wherein said connector comprises
any of:
a flexible connector;
a flexible connector having a relatively rigid center portion and
comparatively flexible ends;
a flexible shaft having alterning grooves;
a spring coil; and
a rigid connector.
29


45. A hearing device, comprising:
a main module comprising any of a microphone, a battery, device controls,
and a signal processing circuit;
a receiver module comprising a receiver; and
a connector for providing an electrical connection between said main
module and said receiver module;
wherein at least two of said main module, receiver module, and connector
are connected by an articulating joint, such that said modules move freely and
independently, one relative to the other within a range of movement and to
freely maintain a position at any point within this range of movement, to permitindependent movement of any of said main module, said receiver module, and
said connector in response to in situ ear canal deformation; and wherein said
main module and said receiver module are each contained in separate,
relatively rigid, non-resilient housings.

46. The hearing device of Claim 8, said acoustic seal further comprising
a canal adapted to provide pressure relief.

47. The hearing device of Claim 8, wherein said acoustic seal is adapted
for deep insertion into the patient's ear canal to minimize or eliminate
occlusion effects.





Description

Note: Descriptions are shown in the official language in which they were submitted.


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Rrticulated Hearing Deuice

BACKGROUND OF THE INVENTION

TECH Nl CAL Fl ELD

The invention relates to hearing aids. More particularly, the invention relates
10 to hearing devices that can be easily and deeply inserted in the ear canal,
while accommodating deformations of the ear canal to provide a comfortable
fit.

DESCRIPTION OF THE PRIOR ART
The trend in the design and manufacture of hearing devices has generally
been towards miniaturization as device components and energy sources
continue to decrease in size and improve in efficiency. This trend is largely
fueled by the demand for a more inconspicuous and cosmetically appealing
20 devices to avoid the stigma of aging and disability associated with hearing
impairment.

Two decades ago, hearing devices were predominately of the Behind-The-
Ear (BTE) type. These devices are placed behind the ear with an acoustic
25 tube connecting the device to an ear mold placed within the ear. Today,
smaller In-The-Ear (ITE) type devices which essentially fit within the concha
of the ear, represent the largest segment of hearing aid types used. Smaller
In-The-Canal (ITC) types, which fit partially in the concha and partially withinthe ear canal, have also become increasingly popular in recent years. In
30 concert with this miniaturization trend, smaller hearing aid devices that fitcompletely within the ear canal, known as Completely-ln-the-Canal (CIC),
are now offered on the market.

In addition to the obvious cosmetic advantages of miniature hearing devices,
35 e g. ITC and CIC types, there are several other advantages that result from
device placement within the ear canal. These advantages include improved
high frequency response, reduced distortion, reduced occlusion effect,
improved sound loc~ tion, reduced wind noise, fewer wax problems that

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typically plug the device receiver, improved use with telephones, and
improved overall sound fidelity due to reduced residual volume in the ear
canal and proximity of the hearing device receiver to the tympanic
membrane ffor example, see Gudmundsen, G.l., Fi~ing J'CIC" Hearing Aids-
Some Practical Pointers, The Hearing Journal, vol. 47, No. 7, 1994, pp. 10,
45-48; and Agnew, J., Aco~lstic Advantages of Deep Canal Hearing Aid
Fit~ings, Hearing Instruments. Vol. 45, No. 8, 1994, pp. 22-25).

Anatomy and Morphology of the Ear Canal
Figs. 1 and 2 show a cross-sectional anatomical view of the ear in the
coronal and transverse planes of the head, respectively. The ear, for the
purpose of this invention, can be described as having three segments. The
first segment represent the medial concha cavity 20 just behind the tragus
15 21 which is relatively large and is surrounded by cartilaginous tissue 22.
The second cavity 23, medial to the aperture 24 of the external acoustic
meatus 11, is generally smaller and is also surrounded by cartilaginous
tissue 22. The third cavity 25 defines the final canal segment near the
tympanic membrane 26 and is surrounded by dense bony tissue 27. The
20 tissue covering the cartilaginous regions 28 is relatively thick and has a well
developed subcutaneous layer thus allowing some expansion to occur. In
contrast, the tissue covering the bony region 29 is relatively thin and
therefore, little or no tolerance for expansion exists in this region. The
cartilaginous region 23 is the major area of cerumen production and
25 accumulation in the ear canal.

The shape of a typical external ear canal, unlike that shown in most artistic
renderings, is rarely cylindrical or conical with a gradual narrowing towards
the tympanic membrane. Instead, most ear canals are non-uniform and
30 have various levels of tortuous contours. Some canals have severe
restrictions in the cartilaginous area.

The ear canal is generally S-shaped, with a first bend 30 occurring
approximately at the aperture of the ear canal and a second bend 31
35 occurring at the cartilaginous-bony junction. The cross sectional diameter ofthe ear canal and the orientation of various regions within the canal are
known to vary considerably from one individual to another. For example, the
length from the aperture 24 to the lateral edge 32 of tympanic membrane 26
ranges from about 20 mm to about 25 mm. The cross sectional shape is

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generally oval. The smallest diameter is generally in the bony region 29 in
the transverse plane and ranges from about 4 mm to about 7 mm. The
largest diameter is in the medial concha region 20 in the coronal plane and
ranges from about 10 mm to about 18 mm.

The morphology of the ear canal reveals substantial deformation within the
cartilaginous area 23 of the ear canal as a result of mandibular motion
associated with talking, chewing, yawning, and biting. This deformation is
generally caused by the asymmetric stresses from the actions of the
10 mandibular condyle 33 (see Fig. 2) on neighboring cartilaginous tissue.
These deformations have radial components, e g. constrictions, and axial
components, i.e. inward and outward motion. These radial and axial
deformations can generally be felt when one inserts a finger in the ear canal
and moves the jaw. In one study, using magnetic resonance imaging (MRI),
15 the deformation was shown to be as much as 25% in the anterior-posterior
direction of the cartilaginous region of the canal (see, for example Oliveira,
R.J., Hammer, B., Stillman, A., Holm, J., Jons, C., Margolis, R.H., A Look at
Ear Canal Changes with Jaw Motion, Ear and Hearing, Vol. 13, No. 6, 1992,
pp. 464-466).
The unique and tortuous nature of individual ear canals, in combination with
the dynamic canal deformations due to mandibular motion, present
unsolved challenges to users of current hearing aid designs, particularly for
deep canal devices. These problems include difficulty in device insertion
25 and removal, discomfort, device retention, and oscillatory feedback. These
problems are further aggravated for persons who suffer abnormal
mandibular function leading to severe ear canal deformations, as in the case
of temporal mandibular joint (TMJ) syndrome.

30 The State of the Art

The substantial inter-subject variability of ear canal shapes has lead the
hearing aid industry to develop hearing devices that are custom
manufactured, based on individual ear canal impressions sent to the
35 manufacturer by the dispensing professional. These custom devices require
an accurate impression to fabricate hearing devices that precisely conform
to the shape of the ear canal. This custom fit attempts to minimize discomfort
to the patient and possible damage to the patient's ear tissue and to prevent
feedback-causing acoustic leakage (see, for example Staab, W.J., Martin,

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L.R., Taking Ear Impressions for Deep Canal Hearing Aid Fittings, The
Hearing Journal, Vol. 47, No. 11, 1994, pp.19-28).

Previews of available miniature devices (see, for example Special Report:
5 Completely-ln-The-Canal Hearing Instruments, The Hearing Journal, Vol.
47, No. 11, 1994, pp. 56-57; and Mini-Canal Hearing Instruments In Review,
Hearing Instruments, Vol. 40, No. 1, 1989, pp. 30-36, 52) reveal an
assortment of hearing devices that require individualized ear impressions
and custom manufacturing. These custom hearing devices are generally
10 made of rigid or semi-rigid acrylic material. Although they may conform to
the shape of the ear canal when they are fully inserted, they present
insertion and removal difficulties, particularly for individuals having tortuouscanals and canals that have non-gradual narrowing.

15 Non-custom hearing devices, e.g. stock hearing aids that do not require
individual ear canal impressions or custom manufacturing, have been also
available on the market. For example, the E-Z EAR hearing device
manufactured by General Instruments, Inc., New Orleans, LA is a stock
hearing device that is marketed as a loaner or a back-up device, because a
20 precise fit of a custom device is considered important for patient comfort and
feedback considerations with current hearing aid designs.

Another stock hearing device is described by Veroba et al (see U.S. patent
No. 4,870,688), in which a rigid core module containing electronic
25 components is combined with a malleable covering module. The modules
are selected from an off-the-shelf assortment to personalize the device fit.
Even though the covering is malleable, the core module is rigid and the
combined structure has a contiguous housing that has only limited ability to
conform to various non-uniform ear canal shapes of a broad population.
30 This is especially true for hearing devices that are deeply inserted in ear
canals that are typically S-shaped.

Another attempt to resolve the problem of conforming a hearing device to the
unique shapes of individual ear canals is disclosed in Oliveira, R.J., Better
35 Hearing Instruments Through Chemistry, Hearing Instruments, Vol. 39, No.
10, 1988. Oliveira proposed attaching a compressible foam ear mold to the
acoustic output of ITE and ITC hearing aids containing a receiver via a
threaded coupler. The foam ear mold contains a semi-rigid tubing that
prevents the foam from fully collapsing and occluding the sound intended for

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delivery to the tympanic membrane. The overall length of the device and the
fixed relationship between the foam ear mold and the hearing device
renders this solution impractical for dealing with various ear canal shapes
and sizes, particularly for deep ear canal device insertion.
Sciarra, M. (see U.S. patent No. 4,539,440) describes an ITC hearing device
having a generally cylindrical body with a resilient stretchable outer layer
that is adjustable to expand and change the diameter of the device. The
device is adjustably expandable such that it fits snugly within the ear canal
10 and is flexibly hinged to permit axial flexibility to accommodate the curvature
of the ear canal. However, Sciarra fails to teach how an essentially
cylindrical shaped device conforms to ear canals that are generally non-
uniform or that are S-shaped.

15 Biermans, J. (see U.S. patent No. 4,937,876) describes a hearing device
that consists of two units. The first unit has a larger cross section and
contains typical hearing aid components, except for the receiver. The
second unit has a smaller diameter and contains the receiver. The two units,
~ which may either be contiguous or separated, are encapsulated by a
20 contiguous housing, presumably of standard rigid or semi-rigid acrylic
material.

Painter, D.S. et al (see UK patent No. GB 2 203 379 A) describes a non-
custom hearing device that initially contains a flexible membrane housing.
25 The device is inserted into the ear canal and a curable material is injected
into the flexible housing, causing the device to harden while conforming to
the shape of the ear canal. Arndt, H. (see U.S. patent No. 5,201,008)
describes a modular hearing device having a housing that includes a
hinged face-plate. The housing contains modular electronic and receiver
30 components. The housing, e.g. hearing aid shell, may be custom or stock.
Stanton, M. (see U.S. patent No. 5,185,802) describes a modular hearing
device having a removable universal interior module that fits within an
exterior shell which is customized for right or left ear canals.

35 The above mentioned designs of miniature hearing devices, e.g. ITC and
CIC, whether fully custom manufactured or stock manufactured for off-the-
shelf dispensing, modular or non-modular, having rigid, semi-rigid, or
malleable housing, do not deal effectively with typical ear canal
deformations that are due to various jaw movements. These dynamic

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deformations in the cartilaginous area lead to many undesira~le e~ects that
are known in the hearing aid industry, including poor device re~er,lion due to
axial pressures on the device, discomfort, pain, and acoustic oscillatory
feedback.
Ward, L.W. etal(see U.S. patent nos. 5,201,007 and 5,031,219) describes a
hearing aid having a rigid acoustic conduction tube that conducts sounds to
the tympanic membrane. The acoustic conduction tube has an external
diameter that is smaller than the ear canal and a flexible flanged tip that
10 seals near the tympanic membrane. This concept, which is known as
minimal contact technology (MCT), alleviates some of the stresses caused
by ear canal deformation via the narrow sound conduction tubing which is in
minimal contact with the tissue that is subject to deformation. The practical
implementation of this concept is described for BTE and ITE types, for
15 example, by Bryant, M. Mueller, H.G., Northern, J.L., Minimal Contact Long
Canal "ITF' Hearing Instruments, Hearing Instruments, Vol. 42, No. 1, 1991,
pp. 12-15, 48. However, the applicability of the MCT concept is
questionable for conventional miniature hearing device designs, e.g ITC or
CIC. Such hearing devices have a contiguous rigid or semi-rigid housing,
20 and may not be comfortably and deeply inserted into a narrow and tortuous
ear canal.

SUMMARY OF THE INVENTION

25 The invention provides a hearing device that incorporates all of the known
advantages of miniature hearing aids that are deeply inserted in the ear
canal with new designs that greatly facilitate device insertion and removal,
while also providing a hearing device having comfortable fit, and reduced
oscillatory feedback during normal and abnormal ear canal deformation.
The invention provides a hearing device having non-contiguous patts that
are highly articulated within the ear canal. The device primarily consists of
three main modules:

3~ (1) A receiver module that delivers acoustic signals within close proximity of
the tympanic membrane;

(2) A main module essentially containing typical hearing aid components,
except the receiver; and

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(3) A connector that routes the amplified electrical signals from the main
module to the receiver module.

5 The connector fits in the cartilaginous area of the ear canal and is articulated
with both the receiver and main modules to accommodate essentially
independent movement of the receiver and main modules when the hearing
device is inserted or removed, and during various jaw movements such as
chewing, yawning, and talking. The connector may be an ~djust~hle shaft to
10 accommodate various ear canal lengths and to allow for incremental
receiver depths within the ear canal.

The receiver module is inserted deeply into the ear canal, preferably in the
bony portion of the ear canal, to provide all of the advantages associated
15 with deep receiver placement. These advantages include improved energy
efficiency and high frequency response, reduced oscillatory feedback,
reduced occlusion effect, reduced distortion, and reduced perceived noise.
The receiver module includes various seals that substantially reduce
acoustic leakage that can cause oscillatory feedback. Furthermore, because
20 the receiver module is completely encapsulated and essentially isolated
from the microphone in the main module, internal acoustic leakage that can
cause oscillatory feedback is also reduced.

In the preferred embodiment of the invention, the main module is loosely
25 fitted in the medial concha area just behind the tragus. The hearing device
is generally invisible unless viewed directly from the side of the ear. The
main module can be highly vented with minimal concerns for oscillatory
feedback. This venting allows occluded own-sounds, ie. sounds that
originate with the individual wearing the device, resonating in the
30 cartilaginous cavity to leak out of the hearing aid, instead of propagating to
the tympanic membrane, as is the case in conventional hearing aids which
have a single contiguous enclosure.

In the preferred embodiment of the invention, the receiver module may
35 connect to any of an assortment of acoustic seal tips to accommodate
variability in ear canal diameters and shapes. The unique features of the
invention, for example articulated parts, adjustable connector length, and
assorted acoustic seal tips, provide a universal hearing device that can be

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dispensed at the point of sale without the need for ear canal impressions or
custom manufacturing.

BRIEF DESCRIPTION OF THE DRAWINGS




Figure 1 is an anatomical view of a right ear in the coronal plane;

Figure 2 is an anatomical view of a right ear in the transverse plane;

10 Figure 3 is a coronal plane view of a right ear showing an articulated
hearing device in accordance with the invention;

Figure 4 is a transverse plane view of a right ear showing an articulated
hearing device in accordance with the invention;
Figure 5 is a view of an articulated hearing device showing response to
radial and axial deformations in the transverse plane in accordance with the
Inventlon;

20 Figures 6a and 6b show a pediatric size main module housing in
accordance with the invention;

Figures 7a and 7b show an adult size main module housing in accordance
with the invention;
2~
Figures 8a and 8b show a large size main module housing in accordance
with the invention;

Figures 9a and 9b provide coronal and transverse views, respectively, of
30 articulated device modules showing module articulation and general
dimensions in accordance with the invention;

Figure 10 is a sectioned view of a receiver module having a built-in soft and
compliant housing in accordance with the invention;
Figure 11 is a sectioned view of a receiver module having a built-in bulbous
tip of soft and compliant material in accordance with the invention;

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Figure 12 is a sectioned view of a receiver module adapted to connect to a
snap-on soft tip in accordance with the invention;

Figure 13 is a sectioned view of a receiver module adapted to connect to a
5 sealing tip via a threaded screw in accordance with the invention;

Figure 14 is a sectioned view of a receiver module having an articulated
sealing tip in accordance with the invention;

10 Figure 15 is a side view of a receiver module having multiple grooves and
sealing rings in accordance with the invention;

Figures 16a-16e are side views of alternative sealing rings for use with the
receiver modules of Figures 15 and 17 in accordance with the invention;
Figure 17 is a side view of a receiver module having a single groove in
accordance with the invention;

Figure 18 is a sectioned view of a receiver module having a sleeve seal in
20 accordance with the invention;

Figure 19 is a sectioned view of an adjustable shaft connector using hollow
screws and a screw sleeve in accordance with the invention;

25 Figure 20 is a sectioned view of an adjustable connector using a telescopic
shaft having a compression nut in accordance with the invention;

Figure 21 is a perspective view of a compressible cylinder around a
connector in accordance with the invention;
Figure 22 is a partially sectioned, perspective view of a compressible
cylinder having a cloth surface in accordance with the invention;

Figure 23 is a coronal view of a completely-in-the-ear-canal configuration of
35 an articulated hearing device in accordance with the invention;

Figure 24 shows single ball-joint articulation with a short connector in
accordance with the invention;

CA 02209068 1998-12-23



Figure 25 shows single balljoint articulation with a long connector in
accordance with the invention;
Figure 26 shows double articulation with a tapered boot and a ball joint in
5 accordance with the invention;
Figure 27 shows a continuous articulation connector in accordance with the
invention;
10 Figure 28 shows a spring coil connector in accordance with the invention;
Figure 29 shows a modular articulated hearing device having detachable parts
in accordance with the invention;
15 Figure 30 shows an articulated hearing device microphone adapted to receive
direct acoustic input from a virtual electroacoustic audiometer in accordance
with the invention;
Figure 31 shows an articulated intra-canal prosthesis in accordance with the
20 invention; and
Figure 32 is a partially exploded view showing sizers for an articulated
hearing aid in accordance with the invention.

DETAll~F~n DESCRIPTION OF THE INVENTION
The hearing device described herein is used for hearing enhancement and
auditory rehabilitation of hearing impaired individuals. The hearing device is
30 also adapted for use as an Intra-Canal-Prosthesis (ICP) in conjunction with a Virtual Electroacoustic Audiometer (VEA).
Figs. 3 and 4 show coronal and transverse views, respectively, of the major
componeqnts of the preferred embodiment of the herein disclosed hearing
35 device 10 inserted in the right ear canal 11.




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CA 02209068 1997-06-27
WO 96/21334 PCT/US95/17113
The main module 12 includes all of the typical components found in a
hearing devices, except for the receiver. These components include a
housing 13, a battery compartment 15, a battery 16, a relatively large vent
18, a signal processor circuit 17 such as the miniature high fidelity non-
5 programmable hybrid ER101-28D manufactured by Etymotic Research of
Elk Grove Village, Illinois, and a low noise microphone 14 such as the
EM4068 manufactured by Knowles Electronics of Itasca, Illinois.

The receiver module 40 includes a receiver 41, a rigid housing 42, and an
10 external housing made of a soft and malleable material 43. The receiver 40
is deeply positioned within the ear canal, preferably in the bony portion 29 of
the canal. The receiver module acoustically seals the device in the bony
area as shown in Figs. 3 and 4. A small vent 44 within the receiver 40 acts
primarily as a pressure relief vent.
A connector 50 contains electrical wires 51 that carry electrical signals
representing processed acoustic signals 19. The connector in the preferred
embodiment o; the invention contains hoiiow screw shafts 52 that are
articulated with the main module 12 via a tapered boot 54, and with the
20 receiver module 40 via another tapered boot 55. The length of the
connector shaft is adjustable via the adjusting screw sleeve 53 to
accommodate variability in ear canal lengths.

Separation of the receiver from the main module, and the receiver's
25 articulation with respect to the main module, allows the receiver to have at
least two degrees of freedom in movement. This freedom of movement
allows essentially independent movement of the receiver module with
respect to the main module, and vice versa. The articulation facilitates deep
device insertion and removal, particularly in narrow and tortuous ear canals.
30 The articulation is also important for accommodating various normal and
abnormal ear canal deformations.

Fig. 5 shows the articulated device as it responds to a particular mandibular
pressure from the condyle 33. This pressure is represented by a vector 60
35 having a radial component 61 and an axial component 62. Ear canal
deformations that are due to direct mandibular pressure are shown by the
dashed line 63. The articulated hearing devicej particularly at the main
module 12 and at the connector 50, shifts in response to the mandibular

CA 02209068 1997-06-27
W O96121334 PCTrUS95/17113
pressure and causes a secondary ear canal deformation, as shown by the
dotted line 65.

Radial pressure generally has minimal effect on the device because the
diameter of the connector 50 is smaller than the diameter of the ear canal, as
shown in the figure. Axial pressure which is generally smaller, causes the
main 12 module, and subsequently the connector 50, to move and rotate in
the direction of the arrow 64, as is shown in the figure. These device
movements have minimal effect on the articul~ted receiver module 40, thus
allowing the receiver module to maintain an acoustic seal with the ear canal,
such that the device is comfortable to wear during various mandibular
motions. This combination of comfort and continuous acoustic sealing
during mandibular motion is not possible with conventional hearing aid
designs that employ contiguous housings and non-articulated parts.
Another advantage of the invention is improved retention of the device within
the ear canal. This is due to the essentially independent movement of
device parts in response to various mandibular motions.

By positioning the receiver in the articulated receiver module, instead of in
the main module as in conventional designs, substantial reduction in the
size of the main module is realized. Typical receivers for use with this
invention include the ES series manufactured by Knowles Electronics which
are 7.5 mm. Iong, 3.58 mm high, and 3 mm wide. The OV series receiver,
also manufactured by Knowles, is slightly larger but its oval shape better
conforms to the natural shape of a typical ear canal. The size reduction due
to repositioning the receiver away from the main module is significant
because it allows a smaller main module to fit deeper in the medial concha
area 20, which is generally more uniform than the lateral concha area 34.
Single or multiple controls 9, e.g. miniature trimmers (see Figs. 6-8) are
typically needed for the non-programmable hearing device and are typically
positioned on the face-plate side 56 of the hearing device. For
programmable hearing devices, a programmable signal processor circuit
17, such as the ER-102, also manufactured by Etymotic Research, may be
used. This arrangement requires a miniature electrical connector (not
shown) on the face plate, such as the CS44-01 manufactured by Microtronic
of Rosklide, Denmark.

CA 02209068 1997-06-27
WO 96/21334 1 ~,1/I).,~S/17113
Other variations of component distribution within the hearing device are
possible without departing from the principles of the invention. For example,
many receivers, such as the ES series mentioned above, contain an
integrated electronic circuit that is used for signal amplification. It is likely
5 that in the future additional circuits or even the entire signal processing
circuit may be fully integrated within the receiver.

Figs. 6-8 show detailed dimensions of a pedial,ic, adult, and large size main
module housing, respectively, in accordance with various embodiments of
10 the invention. The size of the main module in the example embodiments
shown in Figs. 6-8 is largely determined by the battery size. A pediatric-size
device, designed primarily for children, uses battery sizes 5A and 10A; the
adult-size main module uses 10A or 312A battery; and a large-size main
module, designed for large ears or for individuals having severely impaired
15 hearing, requires larger batteries of higher energy capacity, such as battery sizes 312A and 13.

The main module contains a relatively large vent 18 that presents minimal
impedance to own-sourids, versus the higher impedance smaller vent 44 of
20 the receiver module 40. This venting arrangement prevents leakage of own-
sounds into the tympanic membrane. The large vent of the main module, or
venting via loosely inserted device, also improves air circulation to the tissuein the cartilaginous area. The unique design of the articulated hearing
device herein disclosed provides a highly vented device, without such
25 concerns for oscillatory feedback as are common to conventional hearing
devices having a contiguous housing.

Figs. 6-8 show typical dimensions of housings in the preferred embodiment
for pediatric (Figs. 6a and 6b), adult (Figs. 7a and 7b), and large (Figs. 8a
30 and 8b) main modules. These designs were developed from averaged ear
canal impressions taken of twelve adults and two children, including six
pairs of complete impressions taken from adult cadavers. The principal
criteria for the main module design is that it should fit deeply and comfortablywithin the medial concha of most individuals, although an exact match of the
35 main module to the shape of each ear canal is not required.

Figs. 9a and 9b show the preferred articulation angle, range of articulation,
and range of dimensions for the preferred embodiment of the invention in
the coronal (Fig. 9a) and transverse (Fig. 9b) views. The diameters of the

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CA 02209068 1997-06-27
WO g6121334 PCT/US95/17113
main module are approximately 15 mm and 9.5 mm in the coronal and
transverse planes, respectively. The articulation of the main module with the
connector is nominally at angles of about 170~ and about 135~ in the
coronal and transverse planes, respectively, with an additional range of
5 articulation of approximately 30~. The length of the connector is
approximately 5 mm +/-3 mm. The receiver articulates with the connector
approximately with nominal angles of about 190~ and about 225~ in the
coronal and transverse planes, respectively. An additional range of
articulation of approximately 30~ is preferred. The length of the receiver
10 module is approximately 6.5 mm +/-2 mm with diameters of 4.5 mm and 3.5
mm in the coronal plane and transverse plane, respectively.

The invention incorporates several design options that reduce or eliminate
various causes of oscillatory feedback, including:
1. Reduction of Feedback Due To Independent Motion of Main Modules. As
described above, the independent motion of the articulated hearing device
modules prevents oscillatory feedback due to acoustic leakage
conventionally caused by various ear canal deformations. This oscillatory
20 feedback occurs when the microphone of the hearing device receives some
of the acoustic energy that is produced by the receiver.

2. Reduction of Feedback Due To External Acoustic Leakage. External
leakage due to imprecise device fit also represents a common cause of
25 oscillatory feedback. In addition to the basic principles of the articulated
hearing device relating to feedback reduction, the following represent
additional features of the invention that reduce external acoustic leakage
feedback:

30 a. A receiver module 40 having a built-in compliant sealing housing 43, as
shown in Fig. 10, made of a soft material such as medical grade silicone.
The pressure vent 44 may also be used for inserting a probe tube 45 into the
ear canal during real-ear and VEA measurements.

35 b. A receiver module 40 having a built-in sealing bulbous tip 70, as shown
in Fig. 11, also made of a soft compliant material such as medical grade
silicone. A semi-rigid tubing 71 prevents the tip 70 from fully collapsing and
occluding the sound from the receiver port 72.

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CA 02209068 1997-06-27
W O96/21334 PCTAUS95117113
c. A receiver module 40, as shown in Fig. 12, that is adapted to connect to a
snap-on sealing tip 80, which is made of a soft material such as silicone or
foam. The connection to the receiver port 72 is made via snap-on
connectors 81. O, ienlaliol, of the sealing tip 80 with the receiver 41 for probe
5 tube insertion is assured via an alignment insert 82.

d. A receiver module 40, as shown in Fig. 13, that is adapted to connect via
threaded connections 91, 92 to a sealing tip 90, which is made of a soft
material such as silicone or foam.
e. A receiver module 40, as shown ir, ~ig. 14, that is adapted to connect to
an articulated tip 100, which is made of a soft material such as silicone or
foam. The articulation is provided via a ball joint 101 and a ball socket 102.

15 f. A receiver module 40, as shown in Figs. 15 and 17, that is adapted to
connect to multiple or single sealing rings 110, respectively, on multiple or
single groves 111, respectively, on the surface of a receiver 40. The rings
are made of a soft compliant material such as silicone or foam. The rings
~ 110a-110e may have various diameters and/or profiles as desired (see, for
20 example Figs. 1 6a-1 6e).

9. A receiver module 40, as shown in Fig. 18, having a sleeve seal 190 that
is made of a soft compliant material such as silicone or foam.

25 The separable sealing parts, described above, are preferably washable or
disposable.

3. Reduction of Feedback Due To Internal Acoustic Leakage. Another type
of oscillatory feedback is caused by acoustic leakage that is conducted
30 internally from the receiver to the microphone of conventional hearing
devices. The invention substantially reduces this type of feedback because
the receiver is completely encapsulated and is essentially isolated from the
internal components of the main module, particularly the microphone.

35 4. Reduction of Feedback Due To Shell Vibrations. Another type of
feedback that is substantially reduced t y the invention is feedback caused
by receiver vibration that is conducted to the microphone via the contiguous
rigid sheli used in conventional hearing aids. The articulated hearing device

- 1~-

CA 02209068 1997-06-27
WO 96/21334 PCT/US95/17113
consists of separated parts, therefore, there is no contiguous sur~ace to
conduct receiver vibration.

5. Reduction of Feedback Due To Piston Action of High Sound Pressures.
5 This type of feedback, common in hearing devices having very high acoustic
gains in excess of 50 dB, is referred to as the piston action feedback. Such
feedback is caused by high sound pressure levels that are produced in the
ear canal that cause the entire hearing device to vibrate. Sound waves are
externally generated from the vibrating face-plate of the hearing device.
10 When reflective surfaces such as telephone receivers or hands are placed
near the vibrating hearing device, these sound waves can bounce back into
the microphone of the hearing device and cause oscillatory feedback. The
invention substantially decouples the movements of the receiver from the
main module, thus reducing piston action feedback common to conventional
15 hearing aids that have a contiguous housing. Furthermore, the viscoelastic
material incorporated into the connector, as is described in greater detail
below, further reduces piston action feedback.

The receiver module 40 is preferably inserted in the bony region 29 of the
20 ear canal to maximize the electroacoustic benefits associated with close
receiver proximity to the tympanic membrane. For persons having extreme
tissue sensitivity, the receiver may be placed in the deeper portion of the
cartilaginous region 23 of the ear canal, preferably at the junction of the
cartilaginous-bony areas. The depth of receiver insertion may be adjusted
25 using an adjustable length connector. The receiver module 40 may also be
incrementally positioned deeper in the ear canal, via the adjustable
connector, as the individual gradually adapts to the receiver.

An example of an adjustable connector 50 is a turnbuckle shaft having an
30 adjusting screw sleeve 53, as is shown in Fig. 19. The threads of one of the
shafts are reversed to allow for connector 50 expansion or contraction via
the rotation of the adjusting screw sleeve 53, which also has reversed
threads on one of its sides A sheath 112 encapsulates the connector to
protect against dirt and physiological byproducts, e.g. sweat and cerumen.
Another variation of the adjustable connector is the telescopic shaft shown in
Fig. 20, where a compression nut 46 and a compression ring 59 are used to
secure a long shaft 58 to a short screw shaft 57, according to the desired
length of the connector. Other melhods of connector adjustment are

- 16-

CA 02209068 1997-06-27
WO 96121334 PCIIUS95/17113
possible and will be obvious to persons skilled in the art of miniature
mechanics.

In the invention, the connector 50 diameter is less than the diameter of the
5 ear canal in the cartilaginous area to accommodate various ear canal
deformations. The connector may also incorporate a compressible cylinder
120, as shown in Fig. 21 to reduce further the possibility of external acoustic
leakage that causes oscillatory feedback. The cylinder is preferably
disposable and made of a foam material, such as E.A.R., manufactured by
10 Cobot Safety Corporation of Indianapolis, Indiana, or Comply, manufactured
by Hearing Components, Inc. of Maplewood, Minnesota. In addition to
acoustic sealing in the cartilaginous area, the cylinder facilitates cerumen
collection because it is positioned in the primary area of cerumen
production. This arrangement prevents cerumen accumulation in the ear
15 canal, a problem common to many hearing aid users, particularly the
elderly.

Another variation of the cylinder around the connector, shown in Fig. 22,
incorporates a cloth surface 121 on the cylinder 120 to facilitate cerumen
20 collection. The cloth is preferably made of a soft, non-abrasive,
biocompatible material such as cotton.

The main module 12 may also be inserted deeper in the ear canal beyond
the canal aperture 24 and within the cartilaginous area 28, as is shown in
25 Fig. 23. In this completely-in-the-canal (CIC) configuration, the main moduleis preferably loosely fitted in the cartilaginous area of the ear canal. An
extraction line 130, typically made of nylon, facilitates the removal of the
articulated device. The CIC configuration is suitable for persons having
relatively good manual dexterity, who prefer a highly inconspicuous hearing
30 device having maximum cosmetic appeal. The deep-concha configuration,
shown in Figs. 3 and 4, which is also inconspicuous, is especially suitable
for persons having relatively poor manual dexterity.

- Both the CIC and the deep concha hearing device configurations, Figs. 23
35 and 3, respectively, are designed to take advantage of the natural acoustic
features of the concha 34 and pinna 35 areas of the ear. These benefits
include selective frequency amplification and sound loc~li7~tion.


- 17-

CA 02209068 1997-06-27
W O96121334 P~lr~3/17113
The articulation for the hearing device of the invention is achieved by a
variety of means. Fig. 24 shows a single articulation between the main
module 12 and the receiver module 40, with a short connector 50. The
articulation consists of a balljoint mechanism having a ball 140 and a ball
5 socket 141.

Fig. 25 shows a single articulation at the receiver module 40 with a long
connector 50. The balljoint articulation consists of a ball 140 and a ball
socket 141.
Fig. 26 shows double articulations at each end of the connector 50. The
articulation consists of a ball 140 and a ball socket 141 at the receiver
module end of the connector, and a tapered boot 54 at the main module end
of the connector. The boot 54, or the connector in general, may incorporate
1~ a viscoelastic material to isolate mechanical vibration among the device
parts.

The articulation may also be obtained via a flexible connector 40, as is
shown in Fig. 27. The flexible shaft shown provides continuous articulation
20 across the connector part. The grooves 114 may be patterned, as shown, to
provide more articulation at receiver module 40 and main module 12 ends of
the connector, as compared with a relatively more rigid central part of the
connector 50.

25 The articulation may be also obtained via a spring coil 113 connector, as is
shown in Fig. 28. The spring coil connector is preferably made of stainless
steel, where the outside coil diameter is in the range of about 1.5 mm to
about 3 mm, and where wire diameter is in the range of about 0.15 mm to
about 0.3 mm. The pitch of the coil is preferably tight, with a tensile strength30 in the range of about 250 to about 340 pounds per square inch.

Other embodiments of the invention that provide articulation at the receiver
module, main module, or connector are possible and will be obvious to
persons skilled in the art of micro-mechanics and materials.
The preferred embodiment of the invention is a universal hearing device that
does not require custom manufacturing or the taking of individual ear canal
impressions. The main module is designed to be loosely fitted, and
generally fills the relatively compliant outer portions of the ear canal. The

- 18-

CA 02209068 1998-12-23



receiver module provides wearing comfort by articulating when it is inserted
and removed, and during various ear canal deformations. The receiver
module seals individual ear canals of various sizes and shapes via its
malleable housing, or via one of the various acoustic seals discussed above.
S The sealing tips are preferably assorted to allow for customization of the
device at the dispensing site. The assorted sizes of main modules also allow
for a broad physical fitting range, including children, adults, persons having
large ears, and persons who are severely hearing impaired.
In another embodiment of the invention, the device may be custom
m~nllf~ctured according to an ear impression or any other method where the
details of the ear canal can be measured or described. Alternatively, the
device may be partially custom manufactured. For example, the receiver
module or the main module may be fabricated according to a partial
impression of the ear canal representing the part to be customized.
In another embodiment of the invention, the parts of the hearing device are
modular, detachable, and interchangeable for in-office customization and
assembly. Fig. 29 shows a modular hearing aid having an articulated receiver
module and a connector that is detachable from a three-pin connector 150 via
a coupler screw 151 and a coupling nut 152. Otller detachable areas, not
shown, may include the center of the connector, the receiver-connector
junction, and other areas that will be obvious to persons skilled in the art.
2s The microphone of the articulated hearing device may be adapted to receive
direct acoustic .~ from a virtual electroacoustic audiometer, such as
disclosed in U.S. patent application serial nos. 08/292,072 and 08/292,073,
rere~ ced above. As shown in Fig. 30, the microphone 14 is com1ected to a
microphone port 162 that connects to a receiver 161 via an acoustic coupler
160. The receiver 161 is connected to the virtual electroacoustic audiometer
(not shown) which presents acoustic signals directly to the articulated hearing
device for aided hearing evaluation. A probe tube 164 is inserted via a main
module vent 18 and a receiver vent 44, as is shown in Fig. 30. The probe
tube is used to measure the acoustic response in the ear canal near the
tympanic membrane from signals generated via the receiver 40.




19

CA 02209068 1998-12-23



An intra-canal prosthesis (ICP), disclosed in above referenced U.S. patent
application serial no. 08/292,067, is adapted for articulation, as is shown in
Fig. 31. The articulated ICP 170 is provided in the form of an articulated
hearing device having a main module 172 that only contains an electrical
connector 171 which routes electrical signals directly from a virtual
electroacoustic audiometer (not shown), via a connector 175, to ICP receiver
173. A probe tube 164 is inserted in the ICP vent 174. The ICP probe tube
164 is used to measure the acoustic response in the ear canal near the
tympanic membrane from acoustic signals generated via the ICP receiver 173.
The ICP is generally used to perform intra-canal diagnostics and hearing aid
simulation as disclosed in above rer~lellced U.S. patent application serial nos.08/292,067 and 08/292,073. In this embodiment of the invention, the ICP is
adapted to perform unaided, simulated aided hearing evaluation in accordance
with virtual electroacoustic audiometry.
Sizers that represent the articulated hearing device in terms of physical
characteristics, shown in Fig. 32, can be used to predetermine the optimal
physical configuration of the hearing device for an individual prior to ~nal
device insertion. Sizers include main module sizers 180, connector sizers
181, receiver sizers 182, and seal tip sizers 183. The sizer parts are
removably attached, preferably using snap-on connections 184, as shown.
The main module sizer 180 may be directly ~tt~cl1ed to tbe receiver sizer 182
to represent hearing devices that have a very short connector. Other sizer
shapes and articulation methods, representing the articulated hearing device
of the present invention are possible and can be implemented by persons
skilled in the art.
Although the invention is described herein with reference to the prerelled
embodiment, one skilled in the art will readily appreciate that other elements,
materials, and applications may be substituted for those set forth herein
without departing from the spirit and scope of the present invention.
Accordingly, the invention should only be limited by the Claims included
below.





Representative Drawing
A single figure which represents the drawing illustrating the invention.
Administrative Status

For a clearer understanding of the status of the application/patent presented on this page, the site Disclaimer , as well as the definitions for Patent , Administrative Status , Maintenance Fee  and Payment History  should be consulted.

Administrative Status

Title Date
Forecasted Issue Date 1999-07-06
(86) PCT Filing Date 1995-12-27
(87) PCT Publication Date 1996-07-11
(85) National Entry 1997-06-27
Examination Requested 1997-12-12
(45) Issued 1999-07-06
Deemed Expired 2002-12-27

Abandonment History

There is no abandonment history.

Payment History

Fee Type Anniversary Year Due Date Amount Paid Paid Date
Application Fee $150.00 1997-06-27
Request for Examination $200.00 1997-12-12
Maintenance Fee - Application - New Act 2 1997-12-29 $50.00 1997-12-12
Registration of a document - section 124 $100.00 1998-01-05
Registration of a document - section 124 $100.00 1998-03-11
Maintenance Fee - Application - New Act 3 1998-12-29 $50.00 1998-12-04
Final Fee $150.00 1999-03-26
Maintenance Fee - Patent - New Act 4 1999-12-27 $100.00 1999-11-04
Maintenance Fee - Patent - New Act 5 2000-12-27 $150.00 2000-11-03
Owners on Record

Note: Records showing the ownership history in alphabetical order.

Current Owners on Record
DECIBEL INSTRUMENTS, INC.
Past Owners on Record
CALMED TECHNOLOGY, INC.
SHENNIB, ADNAN
URSO, RICHARD
Past Owners that do not appear in the "Owners on Record" listing will appear in other documentation within the application.
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Document
Description 
Date
(yyyy-mm-dd) 
Number of pages   Size of Image (KB) 
Cover Page 1997-09-30 1 58
Abstract 1997-06-27 1 62
Claims 1997-06-27 6 244
Drawings 1997-06-27 14 386
Description 1997-06-27 20 1,143
Description 1998-12-23 20 1,156
Representative Drawing 1999-06-28 1 12
Cover Page 1999-06-28 1 56
Claims 1997-06-28 8 261
Drawings 1997-06-28 14 388
Claims 1998-12-23 8 272
Representative Drawing 1997-09-30 1 15
Correspondence 1999-03-26 1 37
Prosecution-Amendment 1997-12-12 1 37
Assignment 1998-01-05 5 217
Prosecution-Amendment 1998-03-11 1 53
Prosecution-Amendment 1998-10-05 2 3
Prosecution-Amendment 1998-12-23 14 554
Prosecution-Amendment 1999-01-27 3 151
Correspondence 2000-01-07 2 49
Assignment 1997-06-27 4 126
PCT 1997-06-27 13 541
Prosecution-Amendment 1997-06-27 11 353
Correspondence 1997-09-16 1 34
Correspondence 1997-07-18 4 145
Fees 1997-12-12 1 37
Fees 1998-12-04 1 36