EP1643802A2 - Transmission de signaux entre prothèses auditives - Google Patents

Transmission de signaux entre prothèses auditives Download PDF

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Publication number
EP1643802A2
EP1643802A2 EP05108060A EP05108060A EP1643802A2 EP 1643802 A2 EP1643802 A2 EP 1643802A2 EP 05108060 A EP05108060 A EP 05108060A EP 05108060 A EP05108060 A EP 05108060A EP 1643802 A2 EP1643802 A2 EP 1643802A2
Authority
EP
European Patent Office
Prior art keywords
hearing aid
signal
hearing
aid device
wearer
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP05108060A
Other languages
German (de)
English (en)
Other versions
EP1643802A3 (fr
Inventor
Henning Dr. Puder
Andre Steinbuss
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos GmbH
Original Assignee
Siemens Audiologische Technik GmbH
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Siemens Audiologische Technik GmbH filed Critical Siemens Audiologische Technik GmbH
Publication of EP1643802A2 publication Critical patent/EP1643802A2/fr
Publication of EP1643802A3 publication Critical patent/EP1643802A3/fr
Withdrawn legal-status Critical Current

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/55—Electric hearing aids using an external connection, either wireless or wired
    • H04R25/558—Remote control, e.g. of amplification, frequency
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/55—Electric hearing aids using an external connection, either wireless or wired
    • H04R25/554—Electric hearing aids using an external connection, either wireless or wired using a wireless connection, e.g. between microphone and amplifier or using Tcoils
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/55—Communication between hearing aids and external devices via a network for data exchange

Definitions

  • the invention relates to a method for operating a hearing aid system and a hearing aid system having at least one first hearing aid device portable on the head or body of a first hearing aid wearer, a second hearing aid worn on the head or body of a second hearing aid wearer and a third hearing aid worn on the head or body of a third hearing aid wearer, comprising in each case at least one input transducer for receiving an input signal and conversion into an electrical input signal, a signal processing unit for processing and amplifying the electrical input signal and an output transducer for outputting a perceptible from the respective hearing aid wearer as an acoustic signal output signal, wherein a signal from the first hearing aid on the second hearing aid device is transferable.
  • an input signal is recorded by means of an input transducer and converted into an electrical input signal.
  • an input transducer usually serves as an input transducer at least one microphone which receives an acoustic input signal.
  • Modern hearing aids often comprise a microphone system with a plurality of microphones in order to achieve a direction dependent on the direction of arrival of acoustic signals reception, a directional characteristic.
  • the input transducers may also include a telecoil or antenna for receiving electromagnetic input signals.
  • the input signals converted by the input transducer into electrical input signals are fed to a signal processing unit for further processing and amplification. The further processing and amplification takes place to compensate for the individual hearing loss of a hearing aid wearer, as a rule, as a function of the signal frequency.
  • the signal processing unit outputs an electrical output signal, which via an output transducer to the hearing of the hearing aid wearer is supplied so that it perceives the output signal as an acoustic signal.
  • output transducers usually listeners are used, which generate an acoustic output signal.
  • output transducers for generating mechanical vibrations are also known, which directly excite certain parts of the ear, such as the ossicles, to vibrate.
  • output transducers are known which directly stimulate neurons of the ear.
  • hearing aids are becoming more and more reduced in order to increase the acceptance of patients for wearing hearing aids.
  • BTE behind-the-ear devices
  • IDO in-the-ear devices
  • CIC devices Consumer In Canal
  • the human ear must be able to handle many fundamentally different listening situations. Examples of such listening situations are: Quiet environment, conversation, television, driving in the car, telephoning, party and so on. Accordingly, the transmission characteristics of the hearing aids are adapted to the different situations. For this purpose, several different hearing programs can be selected in the hearing aid devices. Usually, these hearing programs can be selected by switches or buttons on the hearing aid itself or by means of a remote control. Increasingly, hearing aids are used which automatically adjust to different listening environments. The reason for this is on the one hand, that the wearing comfort and ease of use is increased.
  • the hearing aid device can automatically switch to a telephone hearing program or the parameters influencing the signal processing in the hearing aid device can be set automatically on the basis of an analysis of an acoustic input signal.
  • Another reason for the need for automatic adaptation to different listening environments lies in the small size, especially of the CIC hearing aids. Such small devices are virtually no longer manually operated without a remote control.
  • a hearing aid system with at least two hearing aid devices is known, between which a signal path for wireless signal transmission is provided.
  • the hearing aid devices each comprise a signal processing unit which can be adapted to different hearing situations, wherein sound field characteristics are generated in the first hearing aid by analysis of the acoustic signals recorded by a microphone of the hearing aid and wherein the sound field characteristics of the first hearing aid to the second hearing aid of Hearing aid system are transmitted to adapt the signal processing in the second hearing aid to the sound field based on the generated in both hearing aids sound field characteristics.
  • a transmitted and amplified acoustic signal by means of a hearing aid speech intelligibility of the hearing aid wearer suffers greatly when the hearing aid wearer is in difficult acoustic situations, such as reverberant environments or in conversational environments, the so-called cocktail party situation.
  • a directional microphone or various noise reduction methods known.
  • FM systems so-called FM systems is known in particular for use in training rooms for the hearing impaired.
  • the acoustic signal is picked up by an external microphone and transmitted as an electromagnetic signal to the hearing aid.
  • Object of the present invention is to improve the range in the signal transmission between hearing aids.
  • a transmission of data is provided between hearing aids of different hearing aid wearers.
  • a wireless signal transmission is preferred, so that the various hearing aid device carriers can move freely in space independently of each other.
  • the hearing aids are equipped for this purpose with appropriate transmitting and receiving devices that can be integrated directly into the hearing aid or designed as, for example, on the body portable external transceiver units.
  • a hearing aid device system according to the invention thus comprises at least three hearing aids worn by different hearing aid wearers.
  • control parameters influencing the signal processing are set in a hearing aid worn by a first hearing aid wearer.
  • the control parameters can be set manually, eg by manually selecting a particular hearing program.
  • the control parameters are automatically adjusted by analysis of the input signal.
  • control parameters may be transferred from the first hearing aid device to one from a second hearing aid device carrier worn second hearing aid for controlling the signal processing in the second hearing aid are transmitted.
  • the transmitted control parameters can relate, for example, to the hearing program set in the first hearing aid. However, this may also be algorithmic estimates, ie internal signal values which have to be estimated with knowledge of the input signals, eg classifier values, parameters of a scene analysis, etc.
  • sound field characteristics are transmitted from the first hearing aid to the second hearing aid.
  • the sound field characteristics are obtained by analyzing the incoming input to the first hearing aid. These include in particular characteristic values with regard to the signal level, the frequency spectrum, the modulation frequency, the modulation depth, the noise components as well as spatial characteristics of acoustic signals of the sound field.
  • the spatial characteristic values of the sound field can in turn be subdivided into coherence, directions of incidence of interference signals, direction of arrival of the useful signal, etc.
  • the sound field characteristics form the data base, on the basis of which the classifier in the hearing aid determines the instantaneous hearing situation.
  • the sound field characteristics generated in the first hearing aid device are transmitted to the second hearing aid device and preferably with sound field characteristics obtained in a similar manner in the second hearing aid device together for determining the hearing situation and for generating parameters for controlling the signal processing in the second hearing aid device used.
  • This is especially interesting when in an acoustic environment a Nutzschalllude is active and a hearing aid wearer is closer to the Nutzschallttle than another.
  • the classifier of the hearing aid device located closer to the useful sound source can then generate better and reliable estimates of the instantaneous hearing situation through the better signal-to-noise ratio in its environment and transmit them to at least one hearing aid device of another hearing aid wearer. which can classify the current hearing situation less reliably. Subsequent methods that require these classifier values can then work better and thus produce a better quality signal for the hearing aid wearer.
  • Another embodiment of the invention provides for the direct transmission of audio signals between the hearing aids of different hearing aid wearers.
  • this method requires very high data transfer rates even when using data compression algorithms; However, it brings advantages if a hearing aid wearer is closer to a useful sound source than another and his hearing aid devices the recorded audio signal - optionally after further processing - sends to one or more other hearing aid wearer.
  • the first hearing aid wearer himself can also be the useful sound source and thus send his voice, recorded with good signal-to-noise ratio, to the microphones of his own first hearing aid as an audio signal to further hearing aid wearer.
  • the signal transmission between the individual hearing aids is preferably wireless.
  • the hearing aids have corresponding transmitting and receiving units for this purpose.
  • the signal transmission is preferably bidirectional, so that each hearing aid device of the hearing aid device system can act as transmitter or receiver. Furthermore, in the transmission of control parameters using a bidirectional connection, an acknowledgment can also be made in the event of a correctly received signal.
  • the hearing aid system according to the invention comprises more than two hearing aids worn by more than two hearing aid wearers.
  • hearing aid devices located between a first hearing aid device and a second hearing aid device located relatively far away can be used to determine the distance between the first two Overcome hearing aids.
  • the intervening hearing aids then perform similar functions as relay stations in radio communications. This means that the signals are not transmitted directly from the first hearing aid device to the second, but first to a third hearing aid located at a lower distance, which then passes the received signals - possibly via other hearing aids - to the distant second hearing aid.
  • larger distances eg in lecture halls, can be easily overcome.
  • One such standard is, for example, the Bluetooth standard.
  • a hearing aid device system with more than two participants improve the analysis options for the relevant sound field with the number of participants and in particular with the distribution of hearing aids in the room.
  • the sound field parameters obtained from the signal analyzes in the individual hearing aids can be exchanged between the hearing aids, so that a comprehensive database for characterizing the relevant sound field is present in each hearing aid , From these data, control parameters for controlling the signal processing in the respective hearing aid devices can then be generated.
  • a master-slave arrangement is also conceivable in which signals generated in the hearing aid devices of a plurality of hearing aid device carriers (sound field characteristics, audio signals) are forwarded to a specific hearing aid device (master) for further evaluation.
  • a hearing aid device of a hearing aid device system can preferably be achieved by programming the respective hearing aid device with a programming device or by operating the hearing aid device, e.g. be determined by means of a remote control. In this case, it can be determined, for example, whether the respective device is a master device or a slave device, whether it merely transmits data to the hearing aid devices of further hearing aid device carriers or even receives data itself and, if appropriate, how the signal processing is influenced by control signals from at least one hearing aid device at least one other hearing aid wearer, is allowed or not.
  • a data transmission with at least one hearing aid device of a further hearing aid wearer may be provided in both hearing aid devices.
  • the data transmission between the first and the second hearing aid preferably takes place wirelessly.
  • FIG. 1 shows three hearing aid device carriers 1, 2 and 3, each with two hearing aid devices 1A, 1B; 2A, 2B; 3A, 3B are supplied. They are not too far away from each other, e.g. together in a room.
  • the hearing aids of each hearing aid wearer each have a transmitting and receiving unit for wireless signal transmission between the hearing aids of the respective hearing aid wearer. This ensures that the hearing aid devices of the respective hearing aid wearer each have a coordinated signal processing. For example, in each case the hearing aids of a hearing aid wearer are operated in the same hearing program.
  • the data transmission between hearing aids is extended to the effect that this not only takes place between the hearing aids of a hearing aid wearer, but is extended to a plurality of hearing aid wearers (participants).
  • a signal transmission between the hearing aid devices 1A and 2A and between the hearing aid devices 1A and 3A is provided in the exemplary embodiment.
  • the hearing aid support 1 is in the immediate vicinity of a useful sound source, e.g. a speaker
  • the hearing aid 1A may receive a signal having a better signal-to-noise ratio than the hearing aids 2A and 3A.
  • the hearing aid wearer carriers 2 and 3 also benefit from an output signal with a high signal-to-noise ratio. Noise sources in the immediate vicinity of the hearing aid wearer 2 or 3 are no longer perceived as a disturber.
  • the hearing aid device 3A thus also assumes the function of a relay station in the signal transmission from the hearing aid device 1A to the hearing aid device 2A. If appropriate, different carrier frequencies of the carrier signals for the signals transmitted by the hearing aid device 1A and the hearing aid device 3A are to be used, as is generally known in the use of radio relay stations.
  • the hearing aid system according to the invention offers a large number of possible variations.
  • all three hearing aid wearers are binaural, ie each supplied with two hearing aids.
  • only one hearing aid device 1A, 2A or 3A is designed for communication with a hearing aid device of another hearing aid wearer.
  • the transmitted signals are forwarded from the hearing aid device 2A to the hearing aid device 2B or from the hearing aid device 3A to the hearing aid device 3B.
  • the hearing aid device 1B receives an acoustic input signal, which then forwarded to the hearing aid 1A and from there, as well as the recorded signal from the hearing aid 1A, is forwarded to the hearing aids 2A and 3A. Then, after reception, the signal picked up by the hearing aid device 1B at the right ear of the hearing aid wearer 1 can be supplied respectively to the right ear of the hearing aid wearer 2 or 3. The same applies to the signal received by the hearing aid 1A on the left ear of the hearing aid wearer 1. Although this procedure requires a very high data transmission rate between the individual hearing aid devices, the spatial hearing impression remains unchanged.
  • the hearing aid wearer carriers 2 and 3 can preferably switch between the audio signal emitted by the hearing aid device 1A and the signals resulting from the microphone signals of the hearing aid devices 2A, 2B or 3A, 3B.
  • the signals originating from the different sources are weighted and added.
  • an audio signal originating from the hearing aid device 1A or 1B can be mixed in an adjustable weighting with the signals emanating from the microphones of the hearing aid devices 2A and 2B.
  • signal transmission between hearing aids of several hearing aid wearers is used to more accurately analyze the listening environment (the sound field) in which the hearing aid wearers are located than is possible with a single hearing aid wearer.
  • sound field characteristics are generated by a respective hearing aid 1A, 2A or 3A from the input signals to the hearing aid, which are then used to classify the sound field.
  • each hearing aid wearer 1, 2 or 3 with two hearing aid devices 1A, 1B; 2A, 2B; 3A, 3B are supplied binaurally, wherein only one hearing aid device in each case communicates with a hearing aid device of another hearing aid wearer and a separate data exchange between the respective two hearing aid devices is provided for tuning the two hearing aid devices of a respective hearing aid wearer.
  • a constellation would also be possible in which all (in the embodiment 6) hearing aids communicate with hearing aids of other hearing aid wearers.
  • FIG. 2 shows the three hearing aid devices 1A, 2A and 3A of the hearing aid device system according to FIG. 1 in a simplified block diagram.
  • Each of the hearing aids has to receive an acoustic input signal and conversion into an electrical signal, a microphone 10, 20 and 30.
  • the microphones each have a signal processing 11, 21 and 31 connected downstream processing and frequency-dependent amplification of the respective input signal and to compensate for the individual
  • the processed signal is finally converted back by means of a handset 12, 22 and 32 into an acoustic signal and delivered into an auditory canal of the hearing aid device carrier 1, 2 or 3.
  • Each of the hearing aids 1A, 2A or 3A further comprises a signal analysis unit 14, 24 and 34 for analyzing the electrical input signal.
  • sound field characteristic values are generated which relate, for example, to the respective signal level, the frequency spectrum, the modulation frequencies, the modulation depths, noise components or spatial characteristics of the sound field, such as coherence, incident direction of interfering or useful signals, etc.
  • parameters for adapting the signal processing in the signal processing units 11, 21 and 31 are generated in the control units 13, 23 and 33, respectively.
  • an exchange of the sound field characteristic values obtained in the hearing aid devices 1A, 2A and 3A between the individual hearing aid devices takes place by means of the transmitting and receiving units 15, 25 and 35, respectively.
  • the transmitted sound field characteristics are used in the signal processing units 13, 23 and 33 to optimize the setting of parameters for controlling the signal processing in the signal processing units 11, 21 and 31.
  • control parameters can also be transmitted between the individual hearing aids, in particular in order to harmonize the signal processing in the individual hearing aids.
  • all hearing aids 1A, 2A and 3A can be operated in the same hearing program coordinated with each other.
  • a further alternative consists in transmitting audio signals between individual hearing aids via the transceiver units 15, 25 or 35 directly from the microphone signals of the respective hearing aid devices 1A, 2A and 3A, respectively. If, for example, an audio signal is transmitted from the hearing aid device 1A to the hearing aid device 2A via the transmitting and receiving unit 15 and received by means of the transmitting and receiving unit 25, then this can be fed to the signal processing unit 21 via the control unit 23 in an adjustable manner, and thus from the be added to the microphone 20 resulting signal.
  • a hearing aid e.g., 3A
  • all three hearing aids can thus generate sound field characteristics from the respective acoustic input signals, the sound field characteristics generated by the hearing aids 1A and 2A being transmitted to the hearing aid 3A for further analysis.
  • the hearing aid device 3A then generates control parameters for the adaptation of the signal processing in the hearing aid devices 1A, 2A, 3A from the sound field characteristics generated in all three hearing aid devices 1A, 2A, 3A.
  • Corresponding control signals are then transmitted from the hearing aid device 3A to the hearing aids 1A and 2A.

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  • Engineering & Computer Science (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Transmitters (AREA)
  • Near-Field Transmission Systems (AREA)
EP05108060A 2004-09-30 2005-09-02 Transmission de signaux entre prothèses auditives Withdrawn EP1643802A3 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102004047759A DE102004047759B3 (de) 2004-09-30 2004-09-30 Verwendung eines Hörhilfegerätesystems mit wenigstens zwei Hörhilfegeräten

Publications (2)

Publication Number Publication Date
EP1643802A2 true EP1643802A2 (fr) 2006-04-05
EP1643802A3 EP1643802A3 (fr) 2009-10-21

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Family Applications (2)

Application Number Title Priority Date Filing Date
EP05108059A Withdrawn EP1643801A3 (fr) 2004-09-30 2005-09-02 Utilisation d'un système de prothèse auditive avec au moins deux prothèses auditives
EP05108060A Withdrawn EP1643802A3 (fr) 2004-09-30 2005-09-02 Transmission de signaux entre prothèses auditives

Family Applications Before (1)

Application Number Title Priority Date Filing Date
EP05108059A Withdrawn EP1643801A3 (fr) 2004-09-30 2005-09-02 Utilisation d'un système de prothèse auditive avec au moins deux prothèses auditives

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US (2) US20060067550A1 (fr)
EP (2) EP1643801A3 (fr)
DE (1) DE102004047759B3 (fr)

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Publication number Publication date
US20060067550A1 (en) 2006-03-30
EP1643802A3 (fr) 2009-10-21
EP1643801A2 (fr) 2006-04-05
DE102004047759B3 (de) 2006-06-01
US20060067549A1 (en) 2006-03-30
EP1643801A3 (fr) 2009-10-21

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