Multi-coil coupling system for hearing aid applications Number:7,522,740 from the United States Patent and Trademark Office (PTO) owispatent A hearing improvement device using a multi-coil coupling system and methods for operating such a device are disclosed. An embodiment of the present invention may use an array microphone to provide highly directional reception. The received audio signal may be filtered, amplified, and converted into a magnetic field for coupling to the telecoil in a conventional hearing aid. Multiple transmit inductors may be used to effectively couple to both in-the-ear and behind-the-ear type hearing aids, and an additional embodiment is disclosed which may be used with an earphone, for users not requiring a hearing aid.<H applications, coupling, Multi, coil, coup, 7522740.html, Patent, pto, 7522740

Title: Multi-coil coupling system for hearing aid applications

Abstract: A hearing improvement device using a multi-coil coupling system and methods for operating such a device are disclosed. An embodiment of the present invention may use an array microphone to provide highly directional reception. The received audio signal may be filtered, amplified, and converted into a magnetic field for coupling to the telecoil in a conventional hearing aid. Multiple transmit inductors may be used to effectively couple to both in-the-ear and behind-the-ear type hearing aids, and an additional embodiment is disclosed which may be used with an earphone, for users not requiring a hearing aid.

Patent Number: 7,522,740 Issued on 04/21/2009 to Julstrom, et al.

Inventors: Julstrom; Stephen D. (Chicago, IL), Drambarean; Viorel (Skokie, IL), Soede; Willem (JL Leiden, NL)
Assignee: Etymotic Research, Inc. (Elk Grove Village, IL)

Appl. No.: 11/345,567

Filed: February 1, 2006

Related U.S. Patent Documents


Application Number	Filing Date	Patent Number	Issue Date
10356290	Jan., 2003	7099486
09752806	Dec., 2000	6694034
60225840	Aug., 2000
60174958	Jan., 2000
60123004	Mar., 1999

Current U.S. Class: 381/331 ; 381/315; 381/322

Current International Class: H04R 25/00 (20060101)

Field of Search: 381/312,315,322,324,326,327,330,331

References Cited [Referenced By]

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Foreign Patent Documents


9804504	Jun., 2000	SE

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Primary Examiner: Ensey; Brian
Attorney, Agent or Firm: McAndrews, Held & Malloy, Ltd.

Parent Case Text

CROSS-REFERENCE TO RELATED APPLICATIONS/INCORPORATION BY REFERENCE

This application is a continuation of prior U.S. patent application Ser. No. 10/356,290 entitled "Multi-Coil Coupling System For Hearing Aid Applications" filed Jan. 31, 2003 now U.S. Pat. No. 7,099,486, which is itself a continuation in part of U.S. patent application Ser. No. 09/752,806, entitled "Transmission Detection and Switch System for Hearing Improvement Applications", filed on Dec. 28, 2000 now U.S. Pat. No. 6,694,034, that in turn makes reference to, claims priority to, and claims the benefit of U.S. Provisional Patent Application Ser. No. 60/174,958 filed Jan. 7, 2000, Ser. No. 60/225,840 filed Aug. 16, 2000, and Ser. No. 60/123,004 filed Mar. 5, 1999, the complete subject matter of each of which is hereby incorporated herein by reference, in its entirety.

Claims

What is claimed is:

1. A method of operating a hearing improvement device suitable for wearing proximate an ear of a user, the method comprising: selecting from a plurality of predefined magnetic field orientations, wherein the plurality of magnetic field orientations comprises a first magnetic field orientation arranged for coupling to a behind the ear type hearing aid and a second magnetic field orientation arranged for coupling to an in the ear type hearing aid; and generating a magnetic field having the selected magnetic field orientation using an electrical signal representative of sound, the magnetic field for coupling to a telecoil of a hearing aid.

2. The method according to claim 1, wherein the plurality of magnetic field orientations comprises two magnetic field orientations.

3. The method according to claim 1, wherein the first inductor is configured to generate the first magnetic field orientation, and a second inductor is configured to generate the second magnetic field orientation.

4. The method according to claim 1, further comprising: converting sound into the electrical signal representative of sound.

5. The method according to claim 1, further comprising: receiving the electrical signal representative of sound.

6. The method according to claim 1, wherein the hearing improvement device is positioned behind an ear of the user.

7. A hearing improvement system comprising: a hearing aid for directing sound into an ear canal of a user; and a housing arranged to fit substantially behind an ear of the user, the housing comprising: a microphone having a relatively greater sensitivity to sound in the direction faced by the user, the microphone for converting sound into an electrical signal; at least one inductor for producing, using the electrical signal, a magnetic field for coupling to a telecoil of the hearing aid, wherein the at least one inductor comprises at least two inductors each generating a magnetic field having a different field orientation; and a battery.

8. The hearing improvement system of claim 7, wherein the hearing aid is a behind-the-ear type hearing aid.

9. The hearing improvement system of claim 7, wherein the housing further comprises switch circuitry for selecting among the at least one inductor.

10. The hearing improvement system of claim 7, wherein the microphone comprises an array microphone.

11. The hearing improvement system of claim 7, wherein the housing further comprises an amplifier for modifying the electrical signal.

12. A hearing improvement device comprising: an amplifier for modifying an electrical signal representative of sound; at least one inductor for generating, from the modified electrical signal, a magnetic field suitable for coupling to the telecoil of a hearing aid; and a housing suitably arranged for wearing proximate an ear of a user, wherein the housing contains the at least one inductor, the amplifier, and a battery, wherein the housing is suitably arranged to fit behind an ear of a user, and wherein the housing is arranged to be collocated with a behind-the-ear (BTE) type hearing aid.

13. The hearing improvement device of claim 12, further comprising a microphone for converting sound into the electrical signal representative of sound.

14. The hearing improvement device of claim 13, wherein the microphone comprises a directional microphone.

15. The hearing improvement device of claim 14, wherein the microphone is an array microphone.

16. The hearing improvement device of claim 12, further comprising switch circuitry for passing the modified electrical signal to a selected one of the at least one inductor.

17. The hearing improvement device of claim 12, further comprising a first electrical connector portion that when mated with a second electrical connector portion enables the passage of the electrical signal representative of sound.

18. The hearing improvement device of claim 12, wherein the at least one inductor comprises at least two inductors each generating a magnetic field having a different field orientation.

19. The hearing improvement device of claim 12, further comprising an ear hook for supporting the device from an ear of a user.

20. A hearing improvement device comprising: an amplifier for modifying an electrical signal representative of sound; at least one inductor for generating, from the modified electrical signal, a magnetic field suitable for coupling to the telecoil of a hearing aid, wherein the at least one inductor comprises at least two inductors each generating a magnetic field having a different field orientation; and a housing suitably arranged for wearing proximate an ear of a user, wherein the housing contains the at least one inductor, the amplifier, and a battery.

21. The hearing improvement device of claim 20, further comprising a microphone for converting sound into the electrical signal representative of sound.

22. The hearing improvement device of claim 21, wherein the microphone comprises a directional microphone.

23. The hearing improvement device of claim 22, wherein the microphone is an array microphone.

24. The hearing improvement device of claim 20, further comprising switch circuitry for passing the modified electrical signal to a selected one of the at least one inductor.

25. The hearing improvement device of claim 20, wherein the housing is suitably arranged to fit behind an ear of a user.

26. The hearing improvement device of claim 25, wherein the housing is arranged to be collocated with a behind-the-ear (BTE) type hearing aid.

27. The hearing improvement device of claim 20, further comprising a first electrical connector portion that when mated with a second electrical connector portion enables the passage of the electrical signal representative of sound.

28. The hearing improvement device of claim 20, further comprising an ear hook for supporting the device from an ear of a user.

Description

This application also makes reference to U.S. Pat. No. 6,009,311, issued Dec. 28, 1999, the complete subject matter of which is hereby incorporated herein by reference in its entirety.

FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT

[N/A]

MICROFICHE/COPYRIGHT REFERENCE

[N/A]

BACKGROUND OF THE INVENTION

Numerous types of hearing aids are known and have been developed to assist individuals with hearing loss. Examples of hearing aid types currently available include behind the ear (BTE), in the ear (ITE), in the canal (ITC) and completely in the canal (CIC) hearing aids. In many situations, however, hearing impaired individuals may require a hearing solution beyond that which can be provided by such a hearing aid using it's internal microphone alone. For example, hearing impaired individuals often have great difficulty carrying on normal conversations in noisy environments, such as parties, meetings, sporting events or the like, involving a high level of background noise. In addition, hearing impaired individuals also often have difficulty listening to audio sources located at a distance from the individual, or to several audio sources located at various distances from the individual and at various positions relative to the individual.

The characteristics and location of a hearing aid internal microphone often results in excessive pickup of ambient acoustical noise. In the past, this has often been overcome by the direct magnetic coupling of a speech signal into a "telecoil", which is often incorporated internally in hearing aids. The telecoil's original purpose was to pick up the stray magnetic field from conventional telephone receivers, which often, although not always, had sufficient strength for efficient direct coupling of the telephone signal. The telecoil's use has expanded to use a receiver in "room loop" systems, where a large room is "looped" with sufficient audio signal-driven cabling to create a reasonably uniform, generally vertically oriented magnetic field within the room. The telecoil has also been used to receive magnetically coupled audio signals from special "neck loops" and thin "silhouette"-style "tele-couplers" fit behind the ear, next to a BTE aid.

A common problem with prior art tele-couplers of the neck loop and silhouette styles has been the difficulty of bathing the telecoil in a magnetic field that is both of sufficient strength and sufficient uniformity in relation to typical relative tele-coupler/telecoil positionings so as ensure a predictable, consistent audio coupling at a volume level that is adequate for comfortable use and that can consistently overcome environmental magnetic noise interference. Additionally, silhouette-style tele-couplers, which are generally designed with BTE aids in mind, have not successfully achieved sufficient field strength at the greater distance needed to reach ITE telecoils, or provided the appropriate field orientation for optimum coupling.

Further, the net frequency response obtained with prior art tele-coupler/telecoil systems has been uncontrolled, unpredictable, and generally not uniform. The combination of the non-uniform frequency characteristics of the field produced by the typical transmitting inductor and the non-uniform frequency response of the typical receiving telecoil results in unsatisfactory overall frequency response for the user.

Further limitations and disadvantages of conventional and traditional approaches will become apparent to one of skill in the art, through comparison of such systems with some aspects of the present invention as set forth in the remainder of the present application with reference to the drawings.

BRIEF SUMMARY OF THE INVENTION

A device, method and/or system for providing hearing improvement, substantially as shown in and/or described in connection with at least one of the figures, as set forth more completely in the claims."

These and other advantages, aspects, and novel features of the present invention, as well as details of illustrated embodiments, thereof, will be more fully understood from the following description and drawings.

BRIEF DESCRIPTION OF SEVERAL VIEWS OF THE DRAWINGS

FIG. 1 is a block diagram of the overall hearing improvement system of the present invention.

FIG. 2 is a block diagram of a more specific embodiment of an overall hearing improvement system in accordance with the present invention.

FIG. 3 is a block diagram of another more specific embodiment of an overall hearing improvement system in accordance with the present invention.

FIG. 4 is a block diagram of a further more specific embodiment of an overall hearing improvement system in accordance with the present invention.

FIG. 5 is a block diagram of a still further more specific embodiment of an overall hearing improvement system in accordance with the present invention.

FIG. 6 is a block diagram of yet another more specific embodiment of an overall hearing improvement system in accordance with the present invention.

FIG. 7 is a block diagram of still another more specific embodiment of an overall hearing improvement system in accordance with the present invention.

FIG. 8 is a block diagram of a further more specific embodiment of an overall hearing improvement system in accordance with the present invention.

FIG. 9 illustrates a component orientation guideline for wireless communication between a secondary audio source and a hearing aid in accordance with the present invention.

FIG. 9A shows a side view of the head of a user wearing an in-the-ear (ITE) type of hearing aid.

FIG. 9B illustrates a side view of the head of a user wearing a behind-the-ear (BTE) type of hearing aid.

FIG. 10 illustrates an advantageous positioning of a transmitting coil relative to a receiving coil based on the guidelines of FIG. 9.

FIG. 11 illustrates an advantageous positioning of a transmitting coil relative to a receiving coil in another embodiment based on the guidelines of FIG. 9.

FIG. 12 illustrates an advantageous positioning of a transmitting coil relative to a receiving coil in yet another embodiment based on the guidelines of FIG. 9.

FIG. 13 illustrates a block diagram of a module for incorporation with a hearing aid.

FIGS. 14A, 14B and 14C illustrate block diagrams for different potential modules for insertion into or incorporation with a hearing aid.

FIGS. 15A, 15B and 15C illustrate block diagrams for different potential modules for insertion into or incorporation with a secondary audio source.

FIG. 16 is a block diagram of one embodiment of a transmission detection and switch system of the present invention.

FIG. 17 is a block diagram of another embodiment of a transmission detection and switch system of the present invention.

FIG. 18 is a block diagram of a further embodiment of a transmission detection and switch system of the present invention.

FIG. 19 illustrates one specific circuit implementation of the transmission detection and switch system embodiment of FIG. 16.

FIG. 20 is a general block diagram of an inductively coupled hearing improvement system in accordance with the present invention.

FIG. 21 illustrates a pulse width modulation system that may be used for the modulation/transmission and reception/limiting blocks of FIG. 20.

FIG. 22 shows a system to obtain large transition spikes with lower, more continuous battery and switch currents in accordance with one embodiment of the present invention.

FIG. 23A illustrates a frequency modulation system in accordance with the present invention.

FIG. 23B illustrates curves that represent the transmitted flux frequency response (lower curve), the received flux frequency response (middle curve), and the net inductor-to-inductor frequency response (upper curve) for the system 2301 of FIG. 23A.

FIG. 24 shows a single stage amplifier that raises an audio frequency input signal strength to an optimum range for a pulse width modulated hybrid in accordance with the present invention.

FIG. 25 provides additional exemplary detail regarding a portion of the block diagram in FIG. 20.

FIG. 26 provides additional exemplary detail regarding another portion of the block diagram in FIG. 20.

FIG. 27 provides additional exemplary detail regarding other portions of the block diagram in FIG. 20.

FIG. 28 shows exemplary detail of the circuitry suggested by the block diagram of FIG. 22.

FIG. 29 shows a block diagram corresponding to the block diagram of FIG. 15B, in which the signal from a directional array microphone is amplified and coupled through one of two inductors to the hearing aid of a user, in accordance with an embodiment of the present invention.

FIG. 30 show a schematic diagram of the circuitry which corresponds to the exemplary embodiment shown in the block diagram of FIG. 29, in accordance with an embodiment of the present invention.

FIG. 30A illustrates a side view of a user wearing an exemplary hearing improvement device, in accordance with an embodiment of the present invention.

FIG. 30B illustrates the use of an embodiment of a hearing improvement device, in accordance with the present invention.

FIG. 31 illustrates the positional relationship during use of a hearing improvement device and an ITE type hearing aid, in accordance with an embodiment of the present invention.

FIG. 32A is a graph which shows the frequency response of a typical amplified telecoil exposed to a magnetic field with a constant, frequency-independent rate-of-change of magnetic flux.

FIG. 32B is a graph of the relative rate-of-change of flux level vs. frequency for a constant applied voltage drive level to a transmit inductor chosen in accordance with an embodiment of the present invention.

FIG. 32C shows a graph of the theoretical transmit inductor drive voltage required to produce a flat frequency response at the output of the receiving telecoil of a typical modern telecoil application.

FIG. 32D shows a graph comparing the theoretical transmit inductor drive voltage require for a flat receiving telecoil frequency response as shown in FIG. 32C, the actual transmit inductor drive voltage in accordance with an embodiment of the present invention, and the expected frequency response at the output of the receive telecoil of a modern hearing aid.

FIG. 33 shows a graph illustrating the field strength of the magnetic field as measured along the length of the BTE transmit inductor of FIG. 31 at different distances from its centerline, in accordance with an embodiment of the present invention.

FIG. 34A and FIG. 34B illustrate two views showing right-ear and left-ear use, respectively, of a BTE type hearing aid with an exemplary hearing improvement device in accordance with an embodiment the present invention.

FIG. 35 illustrates a further embodiment in which an earphone is directly connected to the hearing improvement device, in accordance with the present invention.

FIG. 35A shows a schematic diagram illustrating the interconnection of a pair of earphones suitable for use with the embodiment shown in FIG. 35, in accordance with an embodiment of the present invention.

FIG. 36 illustrates an additional embodiment in which a hearing improvement device is directly coupled to the hearing aid of a user, in accordance with the present invention.

DETAILED DESCRIPTION OF THE INVENTION

FIG. 1 is a block diagram of an overall hearing improvement system 101 of the present invention. A transmission detection and switch system 103 receives signals from both a primary audio source 105 and a secondary audio source 107. The primary audio source 105 may be, for example, a directional or omnidirectional microphone located in a hearing aid. The secondary audio source 107 may be, for example, a directional microphone/transmitter mounted on eyeglasses (or otherwise supported by a hearing aid user), a television or stereo transmitter, a telephone or a microphone/transmitter combination under the control of a talker. In one embodiment, the secondary audio source 107 utilizes a wireless transmission scheme for transmission of signals to the transmission detection and switch system 103. In another embodiment, the secondary audio source 107 is wired to the transmission detection and switch system 103.

In operation, the transmission detection and switch system 103, which may or may not be located within the hearing aid, selects one of signals 109 and 111 (from the primary and secondary audio sources 105 and 107, respectively), and feeds the selected signal as an input 113 to hearing aid circuitry 115. Hearing aid circuitry 115, which may be, for example, a hearing aid amplifier and speaker, in turn generates an audio output 117 for transmission into the ear canal of the hearing aid user.

In one embodiment, when the secondary audio source 107 is selected for transmission into the ear canal of the hearing aid user, the primary audio source 105, i.e., the hearing aid microphone, is completely shut off. In this case, the hearing aid user cannot generally hear any audio received by the primary audio source 105. In another embodiment, however, even when the secondary audio source is selected, the primary audio source 105 is not completely shut off. Instead, the primary audio source 105 is only attenuated so that the hearing aid user can still hear background or room sounds when listening to the secondary audio source 107. Attenuation of the primary audio source 105 as such enables the hearing aid user to listen to the secondary audio source 107 while retaining a room sense or orientation that is provided to the hearing aid user by the primary audio source 105.

FIG. 2 is a block diagram of a more specific embodiment of an overall hearing improvement system in accordance with the present invention. The system 201 comprises a hearing aid 203, which may be one of several types of hearing aids currently available, such as, for example, the BTE, ITE, ITC and CIC hearing aids mentioned above. The hearing aid 203 comprises a housing that incorporates a microphone 207, which may either be a directional microphone, an omni-directional microphone, or a switchable combination of the two. In any case, the microphone 207 acts as a primary audio source for the hearing aid 203.

The hearing aid 203 also comprises a receiver 209 and associated circuitry for receiving wireless signals via an aerial 210. The receiver 209 and aerial 210 combination may be, for example, a radio frequency receiver and antenna or an inductive coil. The hearing aid 203 further comprises circuitry 212 that performs signal detecting, selecting and combining functionality. The circuitry 212 selects either signals received by the hearing aid microphone 207 or by the receiver 209, as discussed more completely herein. The selected signal (or combined signal, if applicable) is next fed to a hearing aid amplifier 206, which amplifies the selected signal, and then to a speaker 208, which converts the selected signal into audio and transmits the audio into the ear canal of a hearing aid user.

In addition to the hearing aid 203, the system 201 of FIG. 2 further comprises a telephone 205, which acts as a secondary audio source for the hearing aid 203. The telephone 205 is hard wired to a traditional telephone network for two-way voice communication via a central office 214. The telephone 205 comprises a typical transceiver 211 that has both a receiver 213 component for receiving voice audio signals from the central office 214 and a transmitter 215 component for transmitting voice audio signals to the central office 214.

The telephone 205 also comprises a second transmitter 216 and associated circuitry, as well as signal combiner circuitry 217 and a data input 219. The transmitter 216 is operatively coupled to the signal combiner circuitry 217, which in turn is operatively coupled to the receiver 213 and the data input 219. Data input 219 may receive data from, for example, a keyboard of the telephone 205 (not shown), memory within the telephone 205, an external computer or the like connected to the telephone 205, or from the central office 214. In any case, such data may be, for example, hearing aid programming information.

The combiner circuitry 217 of the telephone 205 transmits audio signals received by the receiver 213 and/or data signals received at the data input 219, to the transmitter 216. Signals received by the transmitter 216 from the combiner circuitry 217 are in turn transmitted wirelessly to the hearing aid 203 via an aerial 221. The transmitter 216 and aerial 221 combination may similarly be, for example, a radio frequency transmitter and antenna or an inductive coil.

In operation, the telephone 205 is brought into proximity of the ear of a hearing aid user. The circuitry 212 of the hearing aid 203 detects wireless signals being transmitted by the wireless transmission subsystem of the telephone 205. The hearing aid user then, if selection of the wireless signals is applicable, hears directly via the speaker 208 of the hearing aid 203 signals that would otherwise have been picked up via microphone 207 of the hearing aid 203 via a speaker of the telephone 205.

The wireless subsystem of the telephone 205 may be continuously activated, manually activated by a user, or may be automatically activated when the telephone 205 rings, is removed from the base unit, receives voice data, or senses that the telephone is in proximity of the hearing aid 203. In addition, the wireless subsystem of the telephone 205 may also assist the hearing aid user to hear the telephone ring. For example, the wireless scheme may broadcast a higher power signal that can be received by the receiver 209 of the hearing aid 203 for indicating to the wearer that the telephone 205 is ringing.

In any event, as is apparent from the above description, the telephone 205 of the system 201 of FIG. 2 essentially includes two communication subsystems that respectively communicate on two separate and distinct networks, namely the traditional hardwired telephone network and a low powered personal wireless network involving the hearing aid 203.

FIG. 3 is a block diagram of another more specific embodiment of an overall hearing improvement system in accordance with the present invention. The system 301 of FIG. 3 is similar to the system 201 of FIG. 2, in that hearing aid 303 of FIG. 3 may have the same components and functionality of the hearing aid 203 discussed above with respect to FIG. 2. However, in the system 301 of FIG. 3, the secondary audio source is different.

More specifically, the system 301 of FIG. 3 comprises a cordless telephone 305 rather than a corded telephone as found in FIG. 2. The cordless telephone 305 may have the same component(s) comprising the wireless subsystem for communication with the hearing aid as those found in the corded telephone in FIG. 2. Instead of being hardwired to a central office 314, however, the telephone 305 of FIG. 3 has a second wireless subsystem for communicating with a base unit 304, which itself is hardwired to the central office 314.

The base unit 304 comprises a wireless transceiver 331 that has a receiver 333 and a transmitter 335 component, as well as an aerial 337, which may be, for example, an antenna. The cordless telephone 305 similarly comprises a wireless transceiver 311 that has a receiver 313 component and a transmitter 315 component, as well as an aerial 339, which likewise may be, for example, an antenna. Signals received by the receiver 335 from the central office 314 are transmitted by the transmitter 335 via the aerial 337 to the cordless telephone 305. The receiver 313 of the cordless telephone 305 receives the signals via the aerial 339, which signals are then transmitted to signal combiner circuitry 317 of the cordless telephone 305. The signals are then transmitted via transmitter 316 and aerial 321 of the cordless telephone 305 to the hearing aid 303.

Similar to the telephone 205 of FIG. 2, the telephone 305 of FIG. 3 essentially includes two communication subsystems that respectively communicate on two separate and distinct networks. This time, however, the communication subsystems are both (at least partially) wireless. The telephone 305 communicates on two personal wireless networks, namely a higher powered one within a home or other premises (which in turn is hardwired to the main telephone network), and a lower powered one involving the hearing aid 303. In all other respects, however, the telephone 305 may have the same functionality as that discussed above with respect to telephone 205 of FIG. 2.

FIG. 4 is a block diagram of a further more specific embodiment of an overall hearing improvement system in accordance with the present invention. The system 401 of FIG. 4 is similar to the system 301 of FIG. 3, in that hearing aid 403 of FIG. 4 may have the same components and functionality of the hearing aid 203 discussed above with respect to FIG. 2. Again, however, in the system 401 of FIG. 4, the secondary audio source is different.

More specifically, in FIG. 4, the secondary audio source is a cellular telephone 405. Like the cordless telephone in FIG. 3, the cellular telephone 405 may have the same component(s) comprising the wireless subsystem for communication with the hearing aid as those found in the corded telephone in FIG. 2. Instead of wirelessly communicating with a base unit that is hardwired to a central office, however, the cellular telephone 405 communicates with a cell site 404 on a wide area cellular network.

The cell site 404 comprises a wireless transceiver 431 that has a receiver 433 and a transmitter 435 component, as well as an aerial 437, which may be, for example, an antenna. The cellular telephone 405 similarly comprises a wireless transceiver 411 that has a receiver 413 component and a transmitter 415 component, as well as an aerial 439, which likewise may be, for example, an antenna. Signals received via the wide area cellular network by the receiver 435 of the cell site 404 are transmitted by the transmitter 435 via the aerial 437 to the cellular telephone 405. The receiver 413 of the cellular telephone 405 receives the signals via the aerial 439, which signals are then transmitted to signal combiner circuitry 417 of the cellular telephone 405. The signals are then transmitted via transmitter 416 and aerial 421 of the cellular telephone 405 to the hearing aid 403.

Similar to the telephones 205 and 305 of FIGS. 2 and 3, respectively, the telephone 405 of FIG. 4 essentially includes two communication subsystems that respectively communicate on two separate and distinct networks. This time, however, the communication subsystems are both entirely wireless. The cellular telephone 405 not only communicates on a high-powered wide area cellular network, but also a lower powered one involving the hearing aid 403. In all other respects, however, the telephone 405 may have the same functionality as that discussed above with respect to telephone 205 of FIG. 2.

FIG. 5 is a block diagram of a still further more specific embodiment of an overall hearing improvement system in accordance with the present invention. The system 501 of FIG. 5 is similar to the systems 301 of FIG. 3 and 401 of FIG. 4, in that hearing aid 503 of FIG. 5 may have the same components and functionality of the hearing aid 203 discussed above with respect to FIG. 2. In the system 501 of FIG. 5, however, the secondary audio source is different altogether.

More specifically, the secondary audio source of FIG. 5 is an audio transmission module 505. The audio transmission module comprises signal combiner circuitry 517 that is hardwired to an audio source 514. The audio source 514 may be, for example, a stereo or other home entertainment system, movie audio at a movie theatre, car audio, etc. The combiner circuitry 517 of the module 505 transmits audio signals received by the receiver from the audio source 514 and/or data signals received at the data input 519, to the transmitter 516. Signals received by the transmitter 516 from the combiner circuitry 517 are in turn transmitted wirelessly to the hearing aid 503 via an aerial 521. The transmitter 516 and aerial 521 combination may be, for example, a radio frequency transmitter and antenna or an inductive coil.

The audio transmission module 505 may, for example, be located in the seat back of a chair proximate the head position of a person sitting in the chair or in a head-rest of a chair. In operation, the hearing aid user brings the user's ear into proximity of the transmission module 505. The circuitry of the hearing aid 503 detects wireless signals being transmitted by the audio transmission module 505. The hearing aid user then, if selection of the wireless signals is applicable, hears directly from the audio source 514 signals that would otherwise have been picked up via microphone of the hearing aid 503 from audio in the listening room.

The wireless subsystem of the audio transmission module 505 may be continuously activated, manually activated by a user, or may be automatically activated when the module 505 receives audio data or senses that the hearing aid 503 has been brought in proximity of the module 505.

FIG. 6 is a block diagram of yet another more specific embodiment of an overall hearing improvement system in accordance with the present invention. The system 601 of FIG. 6 is similar to the system 501 of FIG. 5, in that hearing aid 603 of FIG. 6 may have the same components and functionality of the hearing aid 203 discussed above with respect to FIG. 2. In addition, the secondary audio source of FIG. 6 is an audio transmission module 605, similar to audio transmission module 505 of FIG. 5. This time, however, the audio transmission module 605 is not hard wired to the audio source. Instead, communication between the audio source 614 and audio transmission module 605 is wireless.

The audio transmission module 605 may have the same component(s) comprising the wireless subsystem for communication with the hearing aid as those found in the audio transmission module 505 of FIG. 5. The audio transmission module 605, however, further comprises a receiver 633 component and an aerial 639, which may be, for example, an antenna, for wirelessly receiving audio signals from the audio source 614. The audio source 614 comprises a transmitter 635 and an aerial 637, which similarly may be, for example, an antenna.

In operation, the audio source 614 transmits audio signals via the aerial 637 to the audio transmission module 605. Signals received by the receiver 633 of the audio transmission module 605 from the audio source 614 are transmitted to combiner circuitry 617, which in turn forwards the audio signals to the transmitter 616. Those signals are in turn transmitted wirelessly to the hearing aid 603 via the aerial 621. Again, the transmitter 616 and aerial 621 combination may be, for example, a radio frequency transmitter and antenna or an inductive coil.

Because the audio transmission module 605 is wireless (and thus need not be wired to the audio source 614), the audio transmission module 605 may be located just about anywhere in a room or premises that is within range of the audio source 614. In addition, the audio transmission module 605, like the cordless telephone of FIG. 3, operates on two separate personal wireless networks, a higher powered one involving the audio source 614 and a lower powered one involving the hearing aid 603. Aside from its wireless receipt of signals from the audio source 614, however, the audio transmission module 605 may operate in the same manner as the audio transmission module 505 of FIG. 5.

FIG. 7 is a block diagram of still another more specific embodiment of an overall hearing improvement system in accordance with the present invention. The system 701 of FIG. 7 is similar to those discussed above, in that hearing aid 703 of FIG. 7 may have the same components and functionality of the hearing aid 203 discussed above with respect to FIG. 2. In addition, the secondary audio source of FIG. 7 is an audio transmission module similar to audio transmission modules 505 and 605 of FIGS. 5 and 6, respectively. In FIG. 7, however, the audio transmission module is a microphone transmission module 705. Instead of receiving audio signals from an audio source, such as a home entertainment system, the microphone transmission module 705 picks up sound from a microphone 704 that is distinct from the microphone of the hearing aid 703. In all other respects, the audio transmission module 705 may operate in the same manner as, and be positioned in the same environments as, the audio transmission module 505 of FIG. 5.

The microphone 704 of the microphone transmission module 705 may be, for example, a directional microphone array or other directional microphone. The microphone transmission module 705 may be worn or otherwise supported by the hearing aid user, or even a talker if the talker is within range for wireless transmission between the microphone transmission module 705 and the hearing aid 703. The microphone transmission module 705 may have the same component(s) comprising the wireless subsystem for communication with the hearing aid as those found in the audio transmission module 505 of FIG. 5. In addition, the microphone transmission module 705 may be continuously activated, manually activated by a user, or may be automatically activated when the module 705 receives audio transmissions or senses that the hearing aid 703 has been brought in proximity of the module 705 (or vice versa).

In operation, the microphone 704 picks up audio and converts it into audio signals. The signals are then transmitted to combiner circuitry 717, which in turn forwards the audio signals to the transmitter 716. Those signals are in turn transmitted wirelessly to the hearing aid 703 via the aerial 721. As previously, the transmitter 716 and aerial 721 combination may be, for example, a radio frequency transmitter and antenna or an inductive coil.

FIG. 8 is a block diagram of a further more specific embodiment of an overall hearing improvement system in accordance with the present invention. The system 801 of FIG. 8 is similar to the system 701 of FIG. 7. In FIG. 8, however, the transmission module 805 receives wireless audio signals from an external audio source, which may be any type of audio source including a "remote" microphone. The transmission module 805 may have the same component(s) comprising the wireless subsystem for communication with the hearing aid as those found in the audio transmission module 505 of FIG. 5. In addition, the audio transmission module 805 may generally operate in the same manner as the audio transmission module 505 of FIG. 5.

The transmission module 805 further comprises a receiver 833 component and/or an infrared receiver 835 component. The transmission module 805 may receive audio signals via the receiver 833 and the aerial 839, which may be, for example, an antenna. Alternatively, the transmission module 805 may receive infrared audio signals via the infrared receiver 835. The signals are then transmitted to combiner circuitry 817, which in turn forwards the audio signals to the transmitter 816. Those signals are in turn transmitted wirelessly to the hearing aid 803 via the aerial 821. As with other embodiments, the transmitter 816 and aerial 821 combination may be, for example, a radio frequency transmitter and antenna or an inductive coil.

FIG. 9 illustrates a component orientation guideline for wireless communication between a secondary audio source and a hearing aid in accordance with the present invention. FIG. 9 specifically illustrates a guideline for the case of inductive wireless transmission. A transmitting coil 901 is shown surrounded by a magnetic field 903. Location of the receiving coil at positions 905 and 909 relative to transmitting coil 901 are advantageous. Locations such as position 907 generally aligned with the magnetic field 903 are also acceptable. Locations such as position 911 aligned perpendicularly to the magnetic field should be avoided, however, due to the null located at such positions.

FIG. 9A shows a side view of the head of a user wearing an in-the-ear (ITE) type of hearing aid 910A. ITE hearing aid 910A contains telecoil 905A, which in the illustration is shown in a vertical orientation. Other orientations of telecoil 910A within ITE hearing aid 910A are possible, however a vertical orientation is most frequently used for compatibility with room loop systems and neck loops, while maintaining adequate compatibility with telephone receivers. As discussed above with respect to FIG. 9, the orientation of telecoil 905A makes it most sensitive to vertically oriented lines of magnetic flux, such as those generated by coil 901 of FIG. 9.

FIG. 9B illustrates a side view of the head of a user wearing a behind-the-ear (BTE) type of hearing aid 910B. This type of hearing aid is positioned behind the curve of the outer ear, between the outer ear and the head. BTE hearing aid 910B as shown is equipped with telecoil 905B. The primarily vertical orientation of BTE hearing aid 910B permits telecoil 905B to be vertically oriented and of greater length and sensitivity than that in the ITE hearing aid of FIG. 9A. As with the ITE hearing aid 910A shown in FIG. 9A, the orientation of telecoil 905B makes it most sensitive to those magnetic fields whose flux lines are primarily vertical, such as the lines of flux created by coil 901 of FIG. 9. There is significant variation, though, among the many commercially available hearing aids in positioning of telecoil 905B along the length of the body.

FIG. 10 illustrates an advantageous positioning of a transmitting coil relative to a receiving coil based on the guidelines of FIG. 9. Transmitting coil 1001, located in or on a glasses frame 1003, is positioned parallel and to the side of a receiving coil 1005 located within a hearing aid 1007.

FIG. 11 illustrates an advantageous positioning of a transmitting coil relative to a receiving coil in another embodiment based on the guidelines of FIG. 9. Transmitting coil 1101, located in seat back or headrest 1103, is similarly positioned parallel and to the side of a receiving coil 1105 located within a hearing aid 1107 when the hearing aid user is in a seated position. This relative positioning will be generally maintained with normal left-right head movements.

FIG. 12 illustrates an advantageous positioning of a transmitting coil relative to a receiving coil in yet another embodiment based on the guidelines of FIG. 9. Transmitting coil 1201, located in telephone 1203, is again similarly positioned parallel and to the side of a receiving coil 1205 located within a hearing aid 1207 when the phone is located proximate the ear in a typical manner.

Certain components used by the hearing improvement system of the present invention may be integrated into a single module that may be manufactured/assembled separately and simply incorporated into or with the hearing aids or secondary audio sources contemplated by the present invention. For example, FIG. 13 illustrates a block diagram of such a module for incorporation with a hearing aid. Module 1301 comprises a hearing aid faceplate 1303 that incorporates a receiver component 1305 having an inductive coil. The faceplate 1303 may also incorporate a hearing aid amplifier 1307 and/or a hearing aid microphone 1309 operatively coupled to the receiving component 1305. The module 1301 may be pre-assembled and sold as a unit to hearing aid manufacturers or sellers who simply install the faceplate 1303 onto a hearing aid shell, and connect the appropriate components. Alternatively, the components 1305, 1307 and 1309 may be integrated into a module that does not include the faceplate 1303 such as, for example, for use with BTE type hearing aids or other types of listening devices.

FIGS. 14A, 14B and 14C illustrate block diagrams for different potential modules for insertion into or incorporation with a hearing aid. FIG. 14A shows a module that is simply comprised of a receiver component having an inductive coil or other type of antenna. FIG. 14B shows a module that likewise has a receiver component having an inductive coil (or other type of antenna), as well as an integrated microphone component. FIG. 14C shows a module that likewise has a receiver component having an inductive coil (or other type of antenna), as well as an integrated amplifier component.

Like the module(s) of FIG. 13, the modules of FIG. 14 may be pre-assembled and sold as a unit to hearing aid or other manufacturers or sellers who simply install the module into the hearing aid or other device and connect the appropriate components.

FIGS. 15A, 15B and 15C illustrate block diagrams for different potential modules for insertion into or incorporation with a secondary audio source. FIG. 15A shows a module that is simply comprised of a transmitter component having an inductive coil or other type of antenna. FIG. 15B shows a module that likewise has a transmitter component having an inductive coil (or other type of antenna), as well as an integrated microphone component. FIG. 15C shows a module that has a receiver component, in addition to a transmitter component having an inductive coil (or other type of antenna). These modules may be pre-assembled and sold as a unit to manufacturers or sellers of secondary audio sources who simply install the module into the secondary audio source and connect the appropriate components.

FIG. 16 is a block diagram of one embodiment of the transmission detection and switch system of the present invention. A transmission detection and switch system 1619, may comprise three basic components, a receiver 1621, a transmission detector 1623 and an electronic switch 1625. The receiver 1621 receives an input signal 1627 from a secondary audio source (not shown). Upon receipt of the input signal 1627 the receiver 1621 generates a detector input signal 1629, as well as an audio output signal 1631 representative of the input signal 1627. The transmission detector 1623 receives the detector input signal 1629, and generates in response a control signal 1633 for the electronic switch 1625. The electronic switch 1625 is controlled by the status of the control signal 1633.

More specifically, for example, if the transmission detector 1623 determines from the detector input signal 1629 that the input signal 1627 represents a desired transmission (e.g., a signal above a certain threshold value), the detector 1623 indicates to the electronic switch 1625, using control signal 1633, that a signal is present. The electronic switch 1625 in turn selects audio output 1631 (representative of the input signal 1627 from the secondary audio source) and provides the audio output 1631 as signal 1635 to hearing aid or other type of circuitry (not shown).

If, on the other hand, the transmission detector 1623 determines from the detector input signal 1629 that the input signal 1629 is not representative of a desired signal (e.g., below a certain threshold value), the detector 1623 indicates to the electronic switch 1625, again using control signal 1633, that no signal is present. The switch then instead selects audio output signal 1637 from the primary audio source (e.g., a hearing aid microphone), and provides the audio output signal 1637 as signal 1635 to the hearing aid or other type of circuitry (not shown).

FIG. 17 is a block diagram of another embodiment of the transmission detection and switch system of the present invention. A transmission detection and switch system 1739 may comprise a receiver 1741 and an electronic switch 1743. The receiver 1741 receives an input signal 1745 from a secondary audio source (not shown). If the input signal 1745 is a desired signal, then receiver 1741 generates a control signal 1747 for the electronic switch 1743. If the input signal 1745 is not a desired signal, then no control signal is generated by the receiver 1741. In either case, the desirability of the signal may be determined by, for example, the receiver 1741 or circuitry associated therewith.

If the electronic switch 1743 receives the control signal 1747 from the receiver 1741, the electronic switch selects receiver output signal 1749, which is an audio output signal representative of input signal 1745 from the secondary audio source (not shown), and provides receiver output signal 1749 as signal 1751 to hearing aid circuitry (not shown).

If, on the other hand, the electronic switch 1743 does not receive the control signal 1747 from the receiver 1741, then the electronic switch selects audio output signal 1753 from the primary audio source (e.g., a hearing aid microphone), and provides the audio output signal 1753 as signal 1751 to the hearing aid circuitry (not shown).

FIG. 18 is a block diagram of a further embodiment of the transmission detection and switch system of the present invention. A transmission detection and switch system 1859 may comprise a receiver 1861 and an electronic switch 1863. The receiver 1861 receives an input signal 1865 from a secondary audio source (not shown), and generates an audio output signal 1867 representative of the input signal 1865 for transmission to electronic switch 1863. The electronic switch 1863 receives the audio output signal 1867, and, if it is determined that the audio output signal 1867 is a desired signal, the electronic switch 1863 provides the audio output signal 1867 as signal 1869 to hearing aid circuitry (not shown). If, on the other hand, it is determined that the audio output signal 1867 is not a desired signal, the electronic switch 1863 provides audio output signal 1871 as signal 1869 to the hearing aid circuitry (not shown). In either case, the desirability of the signal 1867 may be determ