EP2012509B1 - Multicomponent hearing aid system and a method for its operation - Google Patents

Multicomponent hearing aid system and a method for its operation Download PDF

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Publication number
EP2012509B1
EP2012509B1 EP08104397A EP08104397A EP2012509B1 EP 2012509 B1 EP2012509 B1 EP 2012509B1 EP 08104397 A EP08104397 A EP 08104397A EP 08104397 A EP08104397 A EP 08104397A EP 2012509 B1 EP2012509 B1 EP 2012509B1
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EP
European Patent Office
Prior art keywords
hearing aid
interference
aid system
component
operating mode
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.)
Revoked
Application number
EP08104397A
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German (de)
French (fr)
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EP2012509A1 (en
Inventor
Mihail Boguslavskij
Volker Gebhardt
Gottfried Rückerl
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 Pte Ltd
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Siemens Medical Instruments Pte Ltd
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Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/554—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception 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; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception 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; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/49—Reducing the effects of electromagnetic noise on the functioning of hearing aids, by, e.g. shielding, signal processing adaptation, selective (de)activation of electronic parts in hearing aid
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/552—Binaural
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting

Definitions

  • the invention relates to a multi-component hearing aid system and a method for its operation, in particular for data transmission between components of the hearing aid system.
  • Hearing aids are used primarily to allow hearing-impaired patients the most natural hearing and to compensate in this regard usually medically-related disorders of the hearing organs. They have, like most medical aids, to fulfill this functionality, without causing any other adverse effects for their wearer. Such impairments may result, on the one hand, from an inappropriate weight of the hearing aid or from restrictions of movement associated with the wearing of hearing aids.
  • aesthetic aids play a special role in medical aids that have to be arranged in the area of the face or head. This is particularly true since it is often the aim that the environment of a patient equipped in this way should largely remain hidden from the symptoms compensated by the hearing aid.
  • the DE 10 2004 047 759 B3 describes a hearing aid that is intended to improve the transmission and amplification of a useful signal, especially in difficult, ie interference-prone environment.
  • it is proposed to transmit signals between a first hearing aid device carried by a first hearing aid wearer and a second hearing aid device carried by a second hearing aid wearer.
  • the transmitted signal may include control parameters, sound field characteristics or an audio signal.
  • the signal transmission between the first hearing aid device and the second hearing aid device to be transmitted via at least one further hearing aid device, which is carried by at least one further hearing aid device wearer.
  • the third hearing aid fulfills the function of a relay station.
  • the US 5,083,312 discloses a hearing aid system programmable via dual tone multi-frequency (DTMF) signals.
  • the DTMF signals are fed to the hearing aid system via a microphone.
  • a loudspeaker of the hearing aid system can be muted.
  • the EP 1 715 723 A2 describes a binaural hearing aid system with two components to be arranged on each ear, which are interconnected with each other and with a third component via a wireless communication channel. One of the components provides the other components with a shared time signal.
  • the EP 1 463 246 A1 describes a method for data exchange between two transceiver systems via a radio link.
  • Each of the transceiver systems has a transmitter and a receiver. In the case of unidirectional data transmission, the transmitter of one and the receiver of the other transceiver can be switched off.
  • the EP 1 460 769 B1 describes a portable transceiver for transmitting and receiving audio signals having different priority values.
  • the US 2003/0100280 A1 describes a method and a device for suppressing harmonics in a device for wireless data transmission.
  • Hearing aid systems in the sense of the invention are understood below to mean all multi-component hearing aid systems which comprise at least one component to be arranged on or in the ear of a patient, and which comprise a further component which is at least partially and / or temporarily in a communication connection to be worn at the ear Component stands.
  • This further component may be arranged independently of the patient's ear and / or comprise in binaural systems another component to be arranged on or in the other ear of the patient.
  • hearing aids are included, which can be adapted during individual sessions with a hearing care professional with the aid of a suitable programming device to the personal needs of the respective hearing aid wearer and / or have additional equipment, about which the patient himself or another person can make an adjustment or adjustment of certain parameters on the hearing aid itself independently of the hearing care professional.
  • the wireless connection concept entails that, with the exception of systems that can be powered by inductive couplings, each component of a multi-component hearing aid system must have its own power source.
  • each component of a multi-component hearing aid system must have its own power source.
  • it follows from the requirements initially described that such an energy source must be as small and light as possible, but on the other hand must have sufficient capacity to maintain the functionality of the hearing aid system for an extended period of time without requiring frequent maintenance in the meantime.
  • hearing aid systems are generally designed so that at least the components of the hearing aid system worn directly on or in the ear of the patient are characterized by very low energy consumption. This applies to the maintenance of functionality as a medical device as well as to the realization of communication between individual hearing aid components. Standards for an inductive wireless transmission of data between individual components of multi-component hearing device systems have become established for this communication.
  • essential components of a hearing aid system including additional equipment designed for data reception generate electromagnetic emissions during data transmission which act as sources of interference during data transmission between the individual components in the immediate vicinity of the transmission link, in particular of the respective active receiver, ie in inductive systems in the vicinity each active receiving coil, are located.
  • sources of interference are, for example, the inductances of clocked voltage regulators or also the supply and output lines of virtually all clocked electronic circuits.
  • Such circuits are used for example for controlling displays. Devices with displays represent in this connection overall strong emitters.
  • the hearing device handset itself can be added as a further source of interference.
  • a sufficiently large distance of the receiving coil to acting as sources of interference modules can also not be realized in particular in or in the ear to be worn components of hearing aids. Even with additional devices that are not to be worn in the immediate vicinity of the ear, the trend is to integrate a high functionality in the device with minimal dimensions, so that the volume of the assemblies used and their maximum distance from each other should be kept as small as possible.
  • the receiving coil can in principle be placed in a minimum of the expected interference field.
  • orthogonal alignments of interacting coils and / or interfering fields are known. It is also known to make a local interference field compensation by generating defined opposing fields.
  • the object of the invention is to provide a way to securely exchange data between individual components of a multi-component hearing aid system, without having to accept the disadvantages of the prior art in purchasing.
  • a hearing aid system having the features of claim 1 and by a hearing aid component of a multi-component hearing aid system according to claim 11.
  • Claims 2 to 10 indicate advantageous embodiments of a hearing aid system according to the invention.
  • Claims 12 to 15 indicate advantageous embodiments of a hearing aid component according to the invention.
  • Claim 16 gives a method for operating a hearing aid system according to the invention to, and claims 17 to 21 relate to advantageous embodiments of this method.
  • the invention is essentially based on putting identified sources of interference into an operating mode at least during the transmission of data in which a coupling of interference signals into one or all receivers involved in the data transmission is at least attenuated compared with the normal operating mode of these interference sources.
  • This change in the operation mode of sources of interference may include their momentary shutdown, but may also consist in a change in the operating mode of the identified source of interference in which only the emission characteristics of the source of interference change but the functions of the components acting as sources of interference are preserved during data transmission.
  • Such a change may include reducing the noise power by reducing the power injected into the noise source or changing the noise spectrum, which may be associated with a clock change in clocked devices.
  • Typical methods for wireless, in particular an inductive data transmission between the components of the hearing aid system can be advantageously adapted in accordance with the invention so that the time at which at least one transmitter operates, is known exactly. At this time, at least one interference source is then placed in another operating mode to facilitate the reception of the transmitted signals or the data transmission.
  • a minimal configuration for use of the invention thus comprises a multi-component hearing aid system with at least one first component to be arranged on or in the ear of a patient for generating and / or amplifying a hearing stimulus and at least one further component, at least partially and / or temporarily in a wireless communication connection the data transmission can take place, to be worn on or in the ear component, with circuitry Means are included, which can put at least one interference source contained in the hearing aid at least during the transmission of data in an operating mode in which at least one interference source over the normal operating mode at least attenuated coupling of interference takes place in a participating in the data transmission receiver.
  • the reception situation in a receiving component of the hearing aid system ie, for example, an accessory, can be significantly improved at precisely defined times, without significantly increasing the performance of the individual components during normal operation impair if the change in the operating mode of the sources of interference takes place only in short windows in which occurring deviations from the normal operation of the hearing aid system are imperceptible.
  • means may also be included which at least temporarily compensate for the loss of function of a switched-off source of interference. For example, with switching regulators the bridging of downtime by adequately sized backup capacitors done.
  • the change in the operating mode of the identified sources of interference if necessary their shutdown, during the transmission of data in all components of the hearing aid system, which are located during the existence of the wireless communication link in the vicinity of participating recipients.
  • the shutdown or change of the operating mode of the interference sources in both the receiving component, and in the transmitting component has the advantage that the influence of sources of interference in the transmitting component, at a relatively short distance between the transmitter and receiver in the near field interference or Interference in the receiver of the receiving component can cause, reduce or exclude it. An impairment of the transmission of data with design-related very small distances between the individual components of the hearing aid system is thus prevented.
  • Fig. 1 shows a schematic diagram of a hearing aid system according to the invention, consisting of two components.
  • the two components of the hearing aid system are a hearing aid component 1 for sound pressure amplification to be worn on the ear of a patient, as well as an additional device 2 with which the individual acoustic signal is transmitted Parameters of the hearing aid component to be worn on the ear can be set, as can be done for example by means of a remote control of the patient himself.
  • the additional device may also be a programming device of a hearing device acoustician.
  • a communication for data transmission between the hearing aid component 1 and the auxiliary device 2 is required.
  • the attachment 2 is brought close to the hearing aid component 1 worn on the ear, so that it is within the range of the data transmission means located on the hearing aid component 1.
  • the data transmission takes place wirelessly via an inductive data transmission path.
  • at least one coil 3, 4, which can be used as a transmitter and receiver, is located in the hearing device component 1 to be worn on the ear and in the additional device 2.
  • the hearing aid component 1 to be worn on the ear furthermore comprises a receiver module 5, a control unit 6 and a transmitter module 7.
  • Signals arriving at the receiving coil 3 are first fed to the receiver module 5 where they are processed accordingly and supplied to the control unit 6 in the form of usable output signals.
  • Various forms of signal processing take place in the control unit 6 in order to be able to use the received signals in a meaningful manner for the functionality of the hearing aid system.
  • the control unit 6 has means to change the respective operating mode of individual identified sources of interference 8,9,10.
  • sources of interference in particular clocked electronic components, such as switching regulator or other to harmonic emissions prone components, but also components that are directly part of the acoustic transmission path of the hearing aid, act.
  • the acoustic transmission path comprises a microphone 11, an amplifier 12 and a loudspeaker 13 in the form of a receiver to be placed in the ear.
  • the accessory 2 also includes a receiver assembly 14, a control unit 15, a transmitter assembly 16 and other sources of interference 17, 18, including a display 19.
  • the illustrated hearing aid system is designed so that the time at which the coil 3 in the hearing aid component 1 operates as a transmitter, in the auxiliary device 2 is known exactly.
  • a communication protocol is designed so that the hearing aid component 1 always transmits data only upon request by the auxiliary device 2 and never independently initiates a transmission.
  • the additional device 2 which has a powerful power supply and correspondingly a relatively high transmission power, thus sends to the hearing aid component 1 a request in the form of a request to transmit desired data.
  • the relatively high transmission power of the transmitter module 16 of the auxiliary device 2 guarantees that this request can be reliably identified by the hearing device component 1, even if the interference sources 8,9,10,13 in the hearing aid component 1 and the interference sources 17, 18, 19 in the Attachment 2 are unchanged in operation.
  • the control units 6, 15 cause a change in the operating mode of the interference sources 8, 9, 10, 13, 17, 18, 19, in this case, a shutdown.
  • a change in the operating mode of the interference sources 8, 9, 10, 13, 17, 18, 19, in this case, a shutdown During the transmission of the data from the hearing aid component 1 to the auxiliary device 2, all sources of interference 8, 9, 10, 13, 17, 18, 19 which are not directly for transmission or reception now remain both in the transmitting hearing device component 1 and in the receiving auxiliary device 2
  • the data needed for the duration of the transmission so for example 50ms, disabled.
  • the hearing aid component 1 responds exclusively to the request by the attachment 2 with the transmission of the requested data. In this way, an event-controlled change of the operating mode of the interference sources 8, 9, 10, 13, 17, 18, 19 ensures that interference is reduced during the transmission of data between the components 1, 2 of the hearing aid system.
  • suitable sources of interference instead of a shutdown can also be briefly put into an operating state which is possibly less favorable in terms of energy, ie briefly increases the energy consumption of the battery-operated hearing aid component 1, but in which the spurious emissions lie in a frequency range which is uncritical for the receiver.
  • the quality of the communication connection can be improved by the fact that the interference sources 8, 9, 10, 13, 17, 18, 19 are also placed in a low-noise operating condition when the auxiliary device 2 transmits data to the hearing aid component 1.
  • Fig. 2 shows a schematic diagram of a binaural hearing aid system with inventive data transmission.
  • a binaural hearing aid system has two separate hearing device components 1, 21 for amplifying the sound pressure, which are each arranged on an ear of the hearing device wearer. Between these hearing aid components, a communication for data exchange is also required. This results, on the one hand, from the need for parameter adjustment and various status inquiries, which must be carried out regularly, and, on the other hand, from physical circumstances which, for the realization of certain hearing aid functions, arrange the interaction of at least two spaced-apart ones Require microphones.
  • the communication between such hearing aid components usually has to take place at a much shorter time interval than is the case, for example, for setting parameters by means of external accessories.
  • each of the hearing aid components has only a very small battery with limited capacity.
  • each of the two hearing aid components 1, 21 has the same means for maintaining or establishing a communication connection for data exchange, and the communication protocol required for its operation is likewise symmetrical designed.
  • Each of the hearing aid components 1, 21 has a coil 3, 23, which can be used as transmitter and receiver.
  • Each of the hearing aid components 1, 21 further includes a receiver assembly 5, 25, a control unit 6, 26 and a transmitter assembly 7, 27.
  • the linkage of the individual modules can be made analogous to the previous embodiment.
  • the control units 6, 26 in turn have means to change the respective operating mode of individual identified sources of interference 8, 28, 9, 29, 10, 30.
  • Each hearing aid component 1, 21 further includes an acoustic transmission path with a microphone 11, 31, an amplifier 12, 32 and a speaker 13, 33 as a sound pressure generating output unit.
  • control units 6, 26 additionally have means for generating time information, for example via a timer circuit 20, 40, which transmits a time signal to the control unit 6, 26 at least at regular intervals.
  • a communication connection for transmitting different data can be established at precisely the same time by the two hearing aid components 1, 21, whereby a change of the operating mode is again known in the inventive manner during the duration of the existence of this communication connection
  • Noise sources 8, 28, 9, 29, 10, 30 and 13, 33 takes place, as a result of which these interference sources 8, 28, 9, 29, 10, 30, 13, 33 are in an operating mode in which at least one attenuated coupling-in of interference signals takes place in each participating in the data transfer recipients.
  • the communication between the two hearing aid components 1, 21 can thus be largely free from interference, i. even with low transmission power there is a high transmission reliability of the data to be transmitted.
  • Fig. 3 shows a schematic diagram of a binaural hearing aid system according to the invention with an appropriate for data communication additional device.
  • this hearing device system comprises two separate hearing device components 1, 21, which are each arranged on one ear of the hearing aid wearer, and on the other hand, the illustrated hearing aid system comprises an additional device 2, which can establish a communication connection with one of the hearing aid components 21.
  • the communication connection between the two hearing aid components 1, 21 is cyclically produced time-dependent. A change of the operating mode of identified sources of interference 8, 9, 10, 13, 28, 29, 30, 33 takes place in a correspondingly time-dependent manner.
  • the communication between the additional unit 2 and the hearing aid component 21 is event-controlled by a request-response system, whereby at least the request always occurs from the additional device 2 and transmitted with much higher transmission power. Depending on the event, the request changes the operating mode of the identified interference sources 17, 18, 19, 28, 29, 30, 33.
  • the initiation of a communication connection by a request, which is transmitted with high transmission power, is always useful if the querying component of the hearing aid system, in this case the accessory 2, has sufficient energy reserves and the production of this communication connection is not made regularly and / or very often got to.
  • the time-dependent production of a communication connection with simultaneous change of the operating mode relevant sources of interference is always useful when the production of this communication connection must be very frequent and / or regularly and the emission of a relatively much energy consuming request signal to the energy budget of the communicating hearing aid components 1, 21 too much burden would.
  • the hearing aid component 21 has an additional transmitting and receiving coil 41, via which the communication with the auxiliary device 2 can proceed.
  • the communication with the auxiliary device 2 and the other ear-worn hearing aid component 1 via one and the same coil 23.
  • the hearing device components 1, 21 can be adapted directly to the needs of the hearing device wearer without the need for a parameter transfer via the communication connection existing between the hearing aid components 1, 21.

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  • Engineering & Computer Science (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Signal Processing (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Headphones And Earphones (AREA)
  • Small-Scale Networks (AREA)
  • Mobile Radio Communication Systems (AREA)
  • Noise Elimination (AREA)
  • Selective Calling Equipment (AREA)
  • Measurement Of Velocity Or Position Using Acoustic Or Ultrasonic Waves (AREA)
  • Stereophonic System (AREA)

Abstract

The system has a hearing aid component (1) generating and/or amplifying an audio impulse. Accessory units (2, 21) partially and intermittently stay in wireless communication connection to the component. Control units (6, 15, 26) shift interference sources (8-10, 17, 18, 28-30, 33), a loudspeaker (13) and a display (19) during transmission of data in an operating mode. Coupling of interference signals is carried out by one of the sources, in receivers (3, 4, 23, 41) engaged in data transmission in the operating mode, where the coupling is damped with respect to a normal operating mode. An independent claim is also included for a method for operating a multi-component hearing aid system.

Description

Die Erfindung betrifft ein mehrkomponentiges Hörgerätesystem sowie ein Verfahren zu seinem Betrieb, insbesondere zur Datenübertragung zwischen Komponenten des Hörgerätesystems.The invention relates to a multi-component hearing aid system and a method for its operation, in particular for data transmission between components of the hearing aid system.

Hörgeräte dienen in erster Linie dazu, hörgeschädigten Patienten ein möglichst natürliches Hörempfinden zu ermöglichen und diesbezüglich in der Regel medizinisch bedingte Funktionsstörungen der Hörorgane zu kompensieren. Dabei haben sie, wie die meisten medizinischen Hilfsmittel, dieser Funktionalität zu genügen, ohne für ihren Träger anderweitige Beeinträchtigungen herbeizuführen. Derartige Beeinträchtigungen können zum einen aus einem unangemessenen Gewicht des Hörgerätes oder auch aus mit dem Tragen von Hörgeräten verbundenen Bewegungseinschränkungen folgen. Daneben spielen bei medizinischen Hilfsmitteln, die im Bereich des Gesichts bzw. des Kopfes angeordnet werden müssen, ästhetische Gesichtspunkte eine besondere Rolle. Das gilt insbesondere, da häufig angestrebt wird, dass der Umgebung eines derart ausgestatteten Patienten das durch das Hörgerät kompensierte Gebrechen weitgehend verborgen bleiben soll.Hearing aids are used primarily to allow hearing-impaired patients the most natural hearing and to compensate in this regard usually medically-related disorders of the hearing organs. They have, like most medical aids, to fulfill this functionality, without causing any other adverse effects for their wearer. Such impairments may result, on the one hand, from an inappropriate weight of the hearing aid or from restrictions of movement associated with the wearing of hearing aids. In addition, aesthetic aids play a special role in medical aids that have to be arranged in the area of the face or head. This is particularly true since it is often the aim that the environment of a patient equipped in this way should largely remain hidden from the symptoms compensated by the hearing aid.

Die genannten Anforderungen führen zu einer fortschreitenden Gewichtsreduzierung und Miniaturisierung zumindest der in Ohrnähe getragenen Hörgerätekomponenten. Dieser Miniaturisierung sind jedoch aufgrund der zunehmenden Komplexität und Funktionalität moderner Hörgeräte Grenzen gesetzt, weshalb sich mehrkomponentige Systeme etabliert haben, in denen einzelne Funktionen des Hörgeräts in ein Zusatzgerät oder andere unabhängig vom Ohr zu platzierende Komponenten ausgelagert wurden. Um diese ausgelagerten Funktionen dennoch nutzen zu können, ist zumindest teilweise eine Kommunikation zwischen am Ohr des Patienten angeordneten Komponenten des Hörgerätesystems und weiteren Komponenten, die sich an einem anderen Ort befinden können, erforderlich. Insbesondere aus den Komfortanforderungen, die an moderne Hörgeräte gestellt werden, folgt, dass diese Kommunikation zwischen den einzelnen Komponenten eines Hörgerätesystems in der Regel drahtlos erfolgt. Das gilt in gleicher Weise für Hörgerätesysteme, die mehrere an oder in den Ohren anzuordnende Komponenten umfassen, die in eine Kommunikationsverbindung einbezogen werden.The requirements mentioned lead to a progressive weight reduction and miniaturization of at least the hearing aid components worn close to the ear. However, these miniaturization are limited due to the increasing complexity and functionality of modern hearing aids, which is why multi-component systems have been established in which individual functions of the hearing aid were outsourced to an accessory or other components to be placed independently of the ear. In order to still be able to use these outsourced functions, there is at least in part a communication between components of the hearing aid system arranged at the patient's ear and other components which are connected to one another Location may be required. In particular, from the comfort requirements that are placed on modern hearing aids, it follows that this communication between the individual components of a hearing aid system usually takes place wirelessly. This applies equally to hearing aid systems comprising a plurality of components to be arranged on or in the ears, which are incorporated into a communication link.

Die DE 10 2004 047 759 B3 beschreibt ein Hörhilfegerät, das die Übertragung und Verstärkung eines Nutzsignals insbesondere in schwieriger, d. h. störsignal-behafteter, Umgebung verbessern soll. Hierzu wird vorgeschlagen, Signale zwischen einem ersten Hörhilfegerät, das von einem ersten Hörhilfegeräteträger getragen wird, und einem zweiten Hörhilfegerät, das von einem zweiten Hörhilfegeräteträger getragen wird, zu übertragen. Dabei kann das übertragene Signal Steuerparameter, Schallfeld-Kennwerte oder ein Audio-Signal umfassen. Ferner ist es möglich, dass die Signalübertragung zwischen dem ersten Hörhilfegerät und dem zweiten Hörhilfegerät über wenigstens ein weiteres Hörhilfegerät, das von wenigstens einem weiteren Hörhilfegeräteträger getragen wird, zu übertragen. Das dritte Hörhilfegerät erfüllt dabei die Funktion einer Relaisstation.The DE 10 2004 047 759 B3 describes a hearing aid that is intended to improve the transmission and amplification of a useful signal, especially in difficult, ie interference-prone environment. For this purpose, it is proposed to transmit signals between a first hearing aid device carried by a first hearing aid wearer and a second hearing aid device carried by a second hearing aid wearer. The transmitted signal may include control parameters, sound field characteristics or an audio signal. Furthermore, it is possible for the signal transmission between the first hearing aid device and the second hearing aid device to be transmitted via at least one further hearing aid device, which is carried by at least one further hearing aid device wearer. The third hearing aid fulfills the function of a relay station.

Die US 5,083,312 offenbart ein Hörgerätesystem, das über Doppeltonmehrfrequenzsignale (DTMF) programmierbar ist. Die DTMF-Signale werden dem Hörgerätesystem über ein Mikrophon zugeführt. Während der Programmierung kann ein Lautsprecher des Hörgerätesystems stummgeschaltet werden.The US 5,083,312 discloses a hearing aid system programmable via dual tone multi-frequency (DTMF) signals. The DTMF signals are fed to the hearing aid system via a microphone. During programming, a loudspeaker of the hearing aid system can be muted.

Die EP 1 715 723 A2 beschreibt ein binaurales Hörgerätesystem mit zwei an jeweils einem Ohr anzuordnenden Komponenten, die untereinander und mit einer dritten Komponente über einen drahtlosen Kommunikationskanal miteinander verbunden sind. Dabei stellt eine der Komponenten den anderen Komponenten ein gemeinsam genutztes Zeitsignal zur Verfügung.The EP 1 715 723 A2 describes a binaural hearing aid system with two components to be arranged on each ear, which are interconnected with each other and with a third component via a wireless communication channel. One of the components provides the other components with a shared time signal.

Die EP 1 463 246 A1 beschreibt ein Verfahren zum Datenaustausch zwischen zwei Sendeempfangsanlagen über eine Funkverbindung. Jede der Sendeempfangsanlagen weist einen Sender und einen Empfänger auf. Im Fall einer unidirektionalen Datenübertragung kann der Sender der einen und der Empfänger der anderen Sendeempfangsanlage abgeschaltet werden.The EP 1 463 246 A1 describes a method for data exchange between two transceiver systems via a radio link. Each of the transceiver systems has a transmitter and a receiver. In the case of unidirectional data transmission, the transmitter of one and the receiver of the other transceiver can be switched off.

Die EP 1 460 769 B1 beschreibt eine tragbare Sendeempfangsanlage zum Senden und Empfangen von Audiosignalen mit unterschiedlichen Prioritätswerten.The EP 1 460 769 B1 describes a portable transceiver for transmitting and receiving audio signals having different priority values.

Die US 2003/0100280 A1 beschreibt ein Verfahren und eine Vorrichtung zur Unterdrückung von Oberschwingungen in einem Gerät zur drahtlosen Datenübertragung.The US 2003/0100280 A1 describes a method and a device for suppressing harmonics in a device for wireless data transmission.

Unter Hörgerätesystemen im Sinne der Erfindung sind im Folgenden alle mehrkomponentigen Hörgerätesysteme zu verstehen, die mindestens eine am oder im Ohr eines Patienten anzuordnende Komponente umfassen, und die eine weitere Komponente umfassen, die zumindest teilweise und/oder zeitweise in einer Kommunikationsverbindung zur am Ohr zu tragenden Komponente steht. Diese weitere Komponente kann unabhängig vom Ohr des Patienten angeordnet sein und/oder in binauralen Systemen eine weitere am oder im anderen Ohr des Patienten anzuordnende Komponente umfassen. In diesem Sinne sind Hörgeräte umfasst, die während einzelner Sitzungen bei einem Hörgeräteakustiker unter Zuhilfenahme eines geeigneten Programmiergerätes an die persönlichen Bedürfnisse des jeweiligen Hörgeräteträgers angepasst werden können und/oder über Zusatzgeräte verfügen, über die der Patient selbst oder eine weitere Person unabhängig vom Hörgeräteakustiker eine Anpassung bzw. Einstellung bestimmter Parameter am Hörgerät selbst vornehmen kann.Hearing aid systems in the sense of the invention are understood below to mean all multi-component hearing aid systems which comprise at least one component to be arranged on or in the ear of a patient, and which comprise a further component which is at least partially and / or temporarily in a communication connection to be worn at the ear Component stands. This further component may be arranged independently of the patient's ear and / or comprise in binaural systems another component to be arranged on or in the other ear of the patient. In this sense, hearing aids are included, which can be adapted during individual sessions with a hearing care professional with the aid of a suitable programming device to the personal needs of the respective hearing aid wearer and / or have additional equipment, about which the patient himself or another person can make an adjustment or adjustment of certain parameters on the hearing aid itself independently of the hearing care professional.

Das drahtlose Verbindungskonzept bringt es mit sich, dass mit Ausnahme von Systemen, die über induktive Kopplungen mit Energie versorgt werden können, jede Komponente eines mehrkomponentigen Hörgerätesystems über eine eigene Energiequelle verfügen muss. Für Komponenten, die direkt am oder im Ohr eines Patienten getragen werden, folgt aus den anfangs beschriebenen Anforderungen, dass eine derartige Energiequelle möglichst klein und leicht auszulegen ist, andererseits jedoch über eine ausreichende Kapazität verfügen muss, um über einen längeren Zeitraum die Funktionsfähigkeit des Hörgerätesystems zu gewährleisten, ohne zwischenzeitlich häufige Wartungsmaßnahmen erforderlich zu machen. Aus diesem Grund werden Hörgerätesysteme in der Regel so ausgelegt, dass sich zumindest die direkt am oder im Ohr des Patienten getragenen Komponenten des Hörgerätesystems durch einen sehr geringen Energieverbrauch auszeichnen. Das gilt für die Aufrechterhaltung der Funktionalität als medizinisches Hilfsmittel ebenso, wie für die Realisierung der Kommunikation zwischen einzelnen Hörgerätekomponenten. Für diese Kommunikation haben sich Standarts einer induktiven drahtlosen Übertragung von Daten zwischen einzelnen Komponenten mehrkomponentiger Hörgerätesysteme etabliert.The wireless connection concept entails that, with the exception of systems that can be powered by inductive couplings, each component of a multi-component hearing aid system must have its own power source. For components worn directly on or in the ear of a patient, it follows from the requirements initially described that such an energy source must be as small and light as possible, but on the other hand must have sufficient capacity to maintain the functionality of the hearing aid system for an extended period of time without requiring frequent maintenance in the meantime. For this reason, hearing aid systems are generally designed so that at least the components of the hearing aid system worn directly on or in the ear of the patient are characterized by very low energy consumption. This applies to the maintenance of functionality as a medical device as well as to the realization of communication between individual hearing aid components. Standards for an inductive wireless transmission of data between individual components of multi-component hearing device systems have become established for this communication.

Bei der induktiven drahtlosen Übertragung von Daten von einer ohrnah zu tragenden Komponente eines Hörgerätesystems an ein mit einer geeigneten Empfangseinrichtung ausgestattetes Gerät, zum Beispiel ein Zusatzgerät in Form einer Relay-Station, eines Programmiergerätes oder einer Fernbedienung, besteht die Problematik, dass aufgrund der relativ geringen Kapazität, Spannung und Spitzenstrombelastbarkeit üblicherweise eingesetzter Batterien auch die maximale Sendeleistung derartiger ohrnah zu tragender Komponenten eines Hörgerätesystems sehr begrenzt ist. Dadurch ergibt sich eine entsprechend geringe Sendereichweite. Insbesondere für heute gebräuchliche induktive Systeme kommt hinzu, dass im normalerweise verwendeten Nahfeld die Reduzierung der Feldstärke in Abhängigkeit von der Entfernung zum Sender besonders stark ins Gewicht fällt. Entsprechend werden mit heute bekannten induktiven Systemen auf der Strecke von einer am Ohr zu tragenden Komponente eines Hörgerätesystems zu einer Empfangseinrichtung entsprechend ihrer Auslegung nur Distanzen von ca. 30 cm überbrückt. Aufgrund des geringen Pegels des Nutzsignals an der Empfangseinrichtung können schon sehr leistungsarme Störquellen die Übertragungsqualität massiv beeinflussen oder die Identifizierung der zu übertragenden Daten erschweren bzw. verhindern.In the inductive wireless transmission of data from a ear to be worn component of a hearing aid system to a device equipped with a suitable receiving device, such as an accessory in the form of a relay station, a programming device or a remote control, there is the problem that due to the relatively low Capacity, voltage and peak current capacity of commonly used batteries and the maximum transmission power of such ear near-bearing components of a hearing aid system is very limited. This results in a correspondingly low transmission range. Especially for today in use Inductive systems add that in the normally used near field, the reduction of the field strength depending on the distance to the transmitter is particularly significant. Accordingly, only distances of about 30 cm are bridged with inductive systems known today on the route from an ear-to-support component of a hearing aid system to a receiving device according to their design. Due to the low level of the useful signal at the receiving device, very low-power sources of interference can massively influence the transmission quality or make it difficult or impossible to identify the data to be transmitted.

Wesentliche Komponenten eines Hörgerätesystems einschließlich zum Datenempfang ausgelegter Zusatzgeräte erzeugen jedoch konstruktionsbedingt elektromagnetische Emissionen, die während der Datenübertragung als Störquellen wirken und sich während der Datenübertragung zwischen den einzelnen Komponenten in unmittelbarer Nähe der Übertragungsstrecke, insbesondere des jeweils aktiven Empfängers, in induktiven Systemen also in der Nähe der jeweils aktiven Empfangsspule, befinden. Solche Störquellen sind zum Beispiel die Induktivitäten getakteter Spannungsregler oder auch die Versorgungs- und Ausgangsleitungen praktisch aller getakteten elektronischen Schaltkreise. Derartige Schaltkreise kommen beispielsweise zur Ansteuerung von Displays zum Einsatz. Geräte mit Displays stellen in diesem Zusammenhang insgesamt starke Emittenten dar. Im eigentlichen Hörgerät, also in ohrnah zu tragenden Komponenten, kann als weitere Störquelle der Hörgeräte-Hörer selbst hinzukommen.However, essential components of a hearing aid system including additional equipment designed for data reception generate electromagnetic emissions during data transmission which act as sources of interference during data transmission between the individual components in the immediate vicinity of the transmission link, in particular of the respective active receiver, ie in inductive systems in the vicinity each active receiving coil, are located. Such sources of interference are, for example, the inductances of clocked voltage regulators or also the supply and output lines of virtually all clocked electronic circuits. Such circuits are used for example for controlling displays. Devices with displays represent in this connection overall strong emitters. In the actual hearing device, that is to say in components to be worn close to the ear, the hearing device handset itself can be added as a further source of interference.

Es ist bekannt, als Störquellen wirkende Baugruppen abzuschirmen. Eine effektive Schirmung magnetischer Störfelder erfordert jedoch die Verwendung von Bauelementen mit relativ großem Platzbedarf, zum Beispiel in µ-Metallboxen. Insbesondere bei im oder am Ohr zu tragenden Komponenten von Hörgeräten ist der erforderliche Platz dafür meist nicht vorhanden und der damit verbunden Gewichtsnachteil nicht akzeptabel.It is known to shield assemblies acting as sources of interference. However, effective shielding of magnetic interference fields requires the use of devices with a relatively large footprint, for example in μ-metal boxes. Especially when in or on the ear to be worn components of hearing aids, the required space for this is usually not available and the associated weight disadvantage is not acceptable.

Ein hinreichend großer Abstand der Empfangsspule zu als Störquellen wirkenden Baugruppen kann insbesondere bei im oder am Ohr zu tragenden Komponenten von Hörgeräten ebenfalls nicht realisiert werden. Auch bei Zusatzgeräten, die nicht in unmittelbarer Nähe des Ohres zu tragen sind, geht der Trend zur Integration einer hohen Funktionalität im Gerät bei möglichst minimalen Abmessungen, so dass auch hier das Volumen der verwendeten Baugruppen sowie deren maximaler Abstand zueinander möglichst klein gehalten werden sollen.A sufficiently large distance of the receiving coil to acting as sources of interference modules can also not be realized in particular in or in the ear to be worn components of hearing aids. Even with additional devices that are not to be worn in the immediate vicinity of the ear, the trend is to integrate a high functionality in the device with minimal dimensions, so that the volume of the assemblies used and their maximum distance from each other should be kept as small as possible.

Unter der Annahme, dass die lokale Anordnung von Sende- bzw. Empfangsspulen und aller Störquellen im Hörgerät bzw. in den Komponenten des Hörgerätesystems fest und zumindest während der Datenübertragung bekannt ist, kann die empfangende Spule prinzipiell in einem Minimum des zu erwartenden Störfeldes platziert werden. Es sind zum Beispiel orthogonale Ausrichtungen von sich beeinflussenden Spule und/oder Störfeldern bekannt. Es ist außerdem bekannt, durch Erzeugung von definierten Gegenfeldern eine lokale Störfeldkompensation vorzunehmen. Dies führt jedoch zu signifikanten Einschränkungen in Bezug auf Designfreiheit und Miniaturisierungsgrad derartig ausgelegter Geräte.Assuming that the local arrangement of transmitting or receiving coils and all interference sources in the hearing aid or in the components of the hearing aid system is known and at least during the data transmission, the receiving coil can in principle be placed in a minimum of the expected interference field. For example, orthogonal alignments of interacting coils and / or interfering fields are known. It is also known to make a local interference field compensation by generating defined opposing fields. However, this leads to significant limitations in terms of freedom of design and miniaturization of devices designed in this way.

Die Aufgabe der Erfindung besteht darin, eine Möglichkeit anzugeben, sicher Daten zwischen einzelnen Komponenten eines mehrkomponentigen Hörgerätesystems auszutauschen, ohne die Nachteile des Standes der Technik in Kauf nehmen zu müssen.The object of the invention is to provide a way to securely exchange data between individual components of a multi-component hearing aid system, without having to accept the disadvantages of the prior art in purchasing.

Die Aufgabe wird gelöst durch ein Hörgerätesystem mit den Merkmalen von Anspruch 1 und durch eine Hörgerätekomponente eines mehrkomponentigen Hörgerätesystem nach Anspruch 11. Die Ansprüche 2 bis 10 geben vorteilhafte Ausgestaltungen eines erfiridungsgemäßen Hörgerätesystems an. Die Ansprüche 12 bis 15 geben vorteilhafte Ausgestaltungen einer erfindungsgemäßen Hörgerätekomponente an. Anspruch 16 gibt ein Verfahren zum Betrieb eines erfindungsgemäßen Hörgerätesystems an, und die Ansprüche 17 bis 21 betreffen vorteilhafte Ausgestaltungen dieses Verfahrens.The object is achieved by a hearing aid system having the features of claim 1 and by a hearing aid component of a multi-component hearing aid system according to claim 11. Claims 2 to 10 indicate advantageous embodiments of a hearing aid system according to the invention. Claims 12 to 15 indicate advantageous embodiments of a hearing aid component according to the invention. Claim 16 gives a method for operating a hearing aid system according to the invention to, and claims 17 to 21 relate to advantageous embodiments of this method.

Die Erfindung beruht im wesentlichen darauf, identifizierte Störquellen zumindest während der Übertragung von Daten in einen Betriebsmodus zu versetzen, in dem eine gegenüber dem normalen Betriebsmodus dieser Störquellen zumindest abgeschwächte Einkopplung von Störsignalen in einen oder alle an der Datenübertragung beteiligten Empfänger erfolgt. Diese Änderung des Betriebsmodus von Störquellen kann deren kurzzeitige Abschaltung umfassen, aber auch in einer Änderung des Betriebsmodus der identifizierten Störquelle bestehen, in der sich lediglich die Abstrahleigenschaften der Störquelle ändern, die Funktionen der als Störquelle wirkenden Bauelemente jedoch während der Datenübertragung erhalten bleiben. Eine derartige Veränderung kann die Reduzierung der Störleistung durch eine Reduzierung der in die Störquelle eingespeisten Leistung oder eine Veränderung des Störspektrums umfassen, was bei getakteten Bauelementen gegebenenfalls mit einer Taktänderung verbunden ist.The invention is essentially based on putting identified sources of interference into an operating mode at least during the transmission of data in which a coupling of interference signals into one or all receivers involved in the data transmission is at least attenuated compared with the normal operating mode of these interference sources. This change in the operation mode of sources of interference may include their momentary shutdown, but may also consist in a change in the operating mode of the identified source of interference in which only the emission characteristics of the source of interference change but the functions of the components acting as sources of interference are preserved during data transmission. Such a change may include reducing the noise power by reducing the power injected into the noise source or changing the noise spectrum, which may be associated with a clock change in clocked devices.

Typische Verfahren zur drahtlosen, insbesondere einer induktiven Datenübertragung zwischen den Komponenten des Hörgerätesystems können in Einklang mit der Erfindung vorteilhafterweise so adaptiert werden, dass der Zeitpunkt, zu dem mindestens ein Sender arbeitet, genau bekannt ist. Zu diesem Zeitpunkt wird dann zumindest eine Störquelle in einen anderen Betriebsmodus versetzt, um den Empfang der gesendeten Signale bzw. die Datenübertragung zu erleichtern.Typical methods for wireless, in particular an inductive data transmission between the components of the hearing aid system can be advantageously adapted in accordance with the invention so that the time at which at least one transmitter operates, is known exactly. At this time, at least one interference source is then placed in another operating mode to facilitate the reception of the transmitted signals or the data transmission.

Eine Minimalkonfiguration zur Nutzung der Erfindung umfasst somit ein mehrkomponentiges Hörgerätesystem mit mindestens einer ersten am oder im Ohr eines Patienten anzuordnenden Komponente zur Erzeugung und/oder Verstärkung eines Hörreizes und mindestens einer weiteren Komponente, die zumindest teilweise und/oder zeitweise in einer drahtlosen Kommunikationsverbindung, über die eine Datenübertragung erfolgen kann, zur am oder im Ohr zu tragenden Komponente steht, wobei schaltungstechnische Mittel umfasst sind, die mindestens eine im Hörgerätesystem enthaltene Störquelle zumindest während der Übertragung von Daten in einen Betriebsmodus versetzen können, in dem durch diese mindestens eine Störquelle eine gegenüber dem normalen Betriebsmodus zumindest abgeschwächte Einkopplung von Störsignalen in einen an der Datenübertragung beteiligten Empfänger erfolgt.A minimal configuration for use of the invention thus comprises a multi-component hearing aid system with at least one first component to be arranged on or in the ear of a patient for generating and / or amplifying a hearing stimulus and at least one further component, at least partially and / or temporarily in a wireless communication connection the data transmission can take place, to be worn on or in the ear component, with circuitry Means are included, which can put at least one interference source contained in the hearing aid at least during the transmission of data in an operating mode in which at least one interference source over the normal operating mode at least attenuated coupling of interference takes place in a participating in the data transmission receiver.

Mit der Deaktivierung der Störquellen bzw. einer Reduzierung der Störleistung oder einer Manipulation des Störspektrums kann temporär zu genau definierten Zeitpunkten die Empfangssituation in einer empfangenden Komponente des Hörgerätesystems, also beispielsweise einem Zusatzgerät, erheblich verbessert werden, ohne die Leistungsfähigkeit der einzelnen Komponenten im Normalbetrieb merklich zu beeinträchtigen, wenn die Änderung des Betriebsmodus der Störquellen lediglich in kurzen Zeitfenstern erfolgt, in denen auftretenden Abweichungen vom Normalbetrieb des Hörgerätesystems nicht wahrnehmbar sind.With the deactivation of the interference sources or a reduction of the interference power or a manipulation of the interference spectrum, the reception situation in a receiving component of the hearing aid system, ie, for example, an accessory, can be significantly improved at precisely defined times, without significantly increasing the performance of the individual components during normal operation impair if the change in the operating mode of the sources of interference takes place only in short windows in which occurring deviations from the normal operation of the hearing aid system are imperceptible.

In bestimmten Fällen sind auch Änderungen des Betriebsmodus von Störquellen denkbar, die Abweichungen vom Normalbetrieb des Hörgerätesystems bedingen, die oberhalb der Wahrnehmbarkeitsschwelle liegen. Da es sich beispielsweise bei der Datenübertragung von einer ohrnah zu tragenden Komponente eines Hörgerätesystems an ein Zusatzgerät um einen Betriebsfall handelt, der in der normalen Applikation eines Hörgerätesystems sehr selten auftritt, zum Beispiel während einer Programmiersitzung beim Auslesen der Hörgerätedaten oder bei einer Statusabfrage der Hörgerätekomponenten durch eine Fernbedienung, ist die damit verbundene möglicherweise wahrnehmbare Leistungseinschränkung tolerabel. So wird das kurzzeitige Abschalten des Hörgeräte-Hörers oder einer Anzeigeeinheit auf dem Zusatzgerät kaum störende Auswirkungen haben.In certain cases, changes in the operating mode of sources of interference are conceivable, which cause deviations from the normal operation of the hearing aid system, which are above the perception threshold. Since, for example, in the case of data transmission from a component of a hearing aid system close to the ear to an auxiliary device, this is a case of operation which occurs very rarely in the normal application of a hearing aid system, for example during a programming session when the hearing aid data is read or when the hearing device components are queried a remote control, the associated possibly observable performance limitation is tolerable. Thus, the brief shutdown of the hearing device handset or a display unit on the attachment will have little disruptive effects.

Vorteilhafterweise können auch Mittel umfasst sein, die den Funktionsverlust einer abgeschalteten Störquelle zumindest kurzzeitig kompensieren. So kann beispielsweise bei Schaltreglern die Überbrückung der Ausfallzeit durch hinreichend dimensionierte Stützkondensatoren erfolgen.Advantageously, means may also be included which at least temporarily compensate for the loss of function of a switched-off source of interference. For example, with switching regulators the bridging of downtime by adequately sized backup capacitors done.

Vorteilhafterweise erfolgt die Änderung des Betriebsmodus der identifizierten Störquellen, gegebenenfalls deren Abschaltung, während der Übertragung von Daten in allen Komponenten des Hörgerätesystems, die sich während des Bestehens der drahtlosen Kommunikationsverbindung in der Nähe beteiligter Empfänger befinden. Die Abschaltung bzw. Änderung des Betriebsmodus der Störquellen sowohl in der empfangenden Komponente, als auch in der sendenden Komponente hat den Vorteil, dass auch der Einfluss von Störquellen in der sendenden Komponente, die bei relativ geringer Entfernung zwischen Sender und Empfänger auch im Nahbereich Empfangsstörungen oder Interferenzen im Empfänger der empfangenden Komponente bewirken können, verringert oder ausgeschlossen wird. Eine Beeinträchtigung der Übertragung von Daten bei auslegungsbedingt sehr geringen Abständen zwischen den einzelnen Komponenten des Hörgerätesystems wird so vorgebeugt.Advantageously, the change in the operating mode of the identified sources of interference, if necessary their shutdown, during the transmission of data in all components of the hearing aid system, which are located during the existence of the wireless communication link in the vicinity of participating recipients. The shutdown or change of the operating mode of the interference sources in both the receiving component, and in the transmitting component has the advantage that the influence of sources of interference in the transmitting component, at a relatively short distance between the transmitter and receiver in the near field interference or Interference in the receiver of the receiving component can cause, reduce or exclude it. An impairment of the transmission of data with design-related very small distances between the individual components of the hearing aid system is thus prevented.

An Ausführungsbeispielen wird die Erfindung näher erläutert. Es zeigen:

Fig.1
ein Prinzipschaltbild eines erfindungsgemäßen Hörgerätesystems bestehend aus zwei Komponenten;
Fig. 2
ein Prinzipschaltbild eines binauralen Hörgerätesystems mit erfindungsgemäßer Datenübertragung; und
Fig. 3
ein Prinzipschaltbild eines binauralen erfindungsgemäßen Hörgerätesystems mit einem zur Datenkommunikation geeigneten Zusatzgerät.
In embodiments, the invention is explained in detail. Show it:
Fig.1
a schematic diagram of a hearing aid system according to the invention consisting of two components;
Fig. 2
a schematic diagram of a binaural hearing aid system with inventive data transmission; and
Fig. 3
a schematic diagram of a binaural hearing aid system according to the invention with a suitable for data communication attachment.

Fig. 1 zeigt ein Prinzipschaltbild eines erfindungsgemäßen Hörgerätesystems, bestehend aus zwei Komponenten. Die beiden Komponenten des Hörgerätesystems sind eine am Ohr eines Patienten zu tragende Hörgerätekomponente 1 zur Schalldruckverstärkung sowie ein Zusatzgerät 2, mit dem einzelne akustische Parameter der am Ohr zu tragenden Hörgerätekomponente eingestellt werden können, wie das beispielsweise mit Hilfe einer Fernbedienung vom Patienten selbst vorgenommen werden kann. In einer nicht dargestellten Alternative kann das Zusatzgerät auch ein Programmiergerät eines Hörgeräteakustikers sein. Fig. 1 shows a schematic diagram of a hearing aid system according to the invention, consisting of two components. The two components of the hearing aid system are a hearing aid component 1 for sound pressure amplification to be worn on the ear of a patient, as well as an additional device 2 with which the individual acoustic signal is transmitted Parameters of the hearing aid component to be worn on the ear can be set, as can be done for example by means of a remote control of the patient himself. In an alternative, not shown, the additional device may also be a programming device of a hearing device acoustician.

Zur Vornahme der Einstellungen ist eine Kommunikation zur Datenübertragung zwischen der Hörgerätekomponente 1 und dem Zusatzgerät 2 erforderlich. Während der Datenübertragung wird das Zusatzgerät 2 in die Nähe der am Ohr getragenen Hörgerätekomponente 1 gebracht, so dass es sich innerhalb der Reichweite der an der Hörgerätekomponente 1 befindlichen Datenübertragungsmittel befindet. Vorliegend erfolgt die Datenübertragung drahtlos über eine induktive Datenübertragungsstrecke. Zu diesem Zweck befindet sich in der am Ohr zu tragenden Hörgerätekomponente 1 sowie im Zusatzgerät 2 mindestens je eine Spule 3, 4, die als Sender und Empfänger genutzt werden kann. Die am Ohr zu tragende Hörgerätekomponente 1 umfasst des Weiteren eine Empfängerbaugruppe 5, eine Steuereinheit 6 sowie eine Senderbaugruppe 7. An der empfangenden Spule 3 eingehende Signale werden zunächst der Empfängerbaugruppe 5 zugeleitet, dort entsprechend aufbereitet und in Form verwertbarer Ausgangssignale der Steuereinheit 6 zugeführt. In der Steuereinheit 6 erfolgen verschiedene Formen einer Signalverarbeitung, um die empfangenen Signale in für die Funktionalität des Hörgerätesystems sinnvoller Weise nutzen zu können. Des Weiteren verfügt die Steuereinheit 6 über Mittel, den jeweiligen Betriebsmodus einzelner identifizierter Störquellen 8,9,10 zu verändern. Als solche Störquellen können insbesondere getaktete elektronische Komponenten, wie Schaltregler oder andere zu oberwellenreichen Emissionen neigende Bauelemente, aber auch Komponenten, die unmittelbar Bestandteil der akustischen Übertragungsstrecke des Hörgerätes sind, wirken. Vorliegend umfasst die akustische Übertragungsstrecke ein Mikrofon 11, einen Verstärker 12 und einen Lautsprecher 13 in Form eines im Ohr zu platzierenden Hörers. Dieser Lautsprecher 13 kann ebenfalls als Störquelle wirken. Die Identifikation der Störquellen kann an Hand der Bauteilspezifikation oder durch entsprechende Messungen bereits während der Konzeption des Hörgerätessystems erfolgen. Das Zusatzgerät 2 umfasst ebenfalls eine Empfängerbaugruppe 14, eine Steuereinheit 15, eine Senderbaugruppe 16 sowie weitere Störquellen 17, 18, darunter auch ein Display 19.To make the settings, a communication for data transmission between the hearing aid component 1 and the auxiliary device 2 is required. During data transmission, the attachment 2 is brought close to the hearing aid component 1 worn on the ear, so that it is within the range of the data transmission means located on the hearing aid component 1. In the present case, the data transmission takes place wirelessly via an inductive data transmission path. For this purpose, at least one coil 3, 4, which can be used as a transmitter and receiver, is located in the hearing device component 1 to be worn on the ear and in the additional device 2. The hearing aid component 1 to be worn on the ear furthermore comprises a receiver module 5, a control unit 6 and a transmitter module 7. Signals arriving at the receiving coil 3 are first fed to the receiver module 5 where they are processed accordingly and supplied to the control unit 6 in the form of usable output signals. Various forms of signal processing take place in the control unit 6 in order to be able to use the received signals in a meaningful manner for the functionality of the hearing aid system. Furthermore, the control unit 6 has means to change the respective operating mode of individual identified sources of interference 8,9,10. As such sources of interference in particular clocked electronic components, such as switching regulator or other to harmonic emissions prone components, but also components that are directly part of the acoustic transmission path of the hearing aid, act. In the present case, the acoustic transmission path comprises a microphone 11, an amplifier 12 and a loudspeaker 13 in the form of a receiver to be placed in the ear. This speaker 13 can also act as a source of interference. The identification of the sources of interference can be based on the component specification or by appropriate measurements already during the conception of the hearing aid system. The accessory 2 also includes a receiver assembly 14, a control unit 15, a transmitter assembly 16 and other sources of interference 17, 18, including a display 19.

Das dargestellte Hörgerätesystem ist so ausgelegt, dass der Zeitpunkt, zu dem die Spule 3 in der Hörgerätekomponente 1 als Sender arbeitet, im Zusatzgerät 2 genau bekannt ist. Zu diesem Zweck ist ein Kommunikationsprotokoll so ausgelegt, dass die Hörgerätekomponente 1 stets nur auf eine Anfrage durch das Zusatzgerät 2 Daten sendet und nie selbständig eine Übertragung initiiert. Das Zusatzgerät 2, das über eine leistungsfähige Stromversorgung und entsprechend über eine relativ hohe Sendeleistung verfügt, sendet somit an die Hörgerätekomponente 1 eine Anfrage in Form einer Aufforderung zur Übertragung gewünschter Daten. Die relativ hohe Sendeleistung der Senderbaugruppe 16 des Zusatzgerätes 2 garantiert dabei, dass diese Aufforderung zuverlässig von der Hörgerätekomponente 1 identifiziert werden kann, auch wenn die Störquellen 8,9,10,13 in der Hörgerätekomponente 1 und die Störquellen 17, 18, 19 in dem Zusatzgerät 2 unverändert in Betrieb sind. Zeitgleich mit der Anfrage veranlassen die Steuereinheiten 6, 15 eine Änderung im Betriebsmodus der Störquellen 8, 9, 10, 13, 17, 18, 19, in diesem Fall eine Abschaltung. Während der Übertragung der Daten von der Hörgerätekomponente 1 zum Zusatzgerät 2 bleiben nun sowohl in der sendenden Hörgerätekomponente 1 als auch im empfangenden Zusatzgerät 2 alle Störquellen 8, 9, 10, 13, 17, 18, 19, die nicht unmittelbar zum Senden bzw. Empfangen der Daten benötigt werden, für die Dauer der Übertragung, also beispielsweise für 50ms, deaktiviert. Die Hörgerätekomponente 1 reagiert ausschließlich auf die Anforderung durch das Zusatzgerät 2 mit dem Senden der angeforderten Daten. Auf diese Weise wird durch eine ereignisgesteuerte Änderung des Betriebsmodus der Störquellen 8, 9, 10, 13, 17, 18, 19 gesichert, dass während der Übertragung von Daten zwischen den Komponenten 1, 2 des Hörgerätesystems Störeinflüsse reduziert werden.The illustrated hearing aid system is designed so that the time at which the coil 3 in the hearing aid component 1 operates as a transmitter, in the auxiliary device 2 is known exactly. For this purpose, a communication protocol is designed so that the hearing aid component 1 always transmits data only upon request by the auxiliary device 2 and never independently initiates a transmission. The additional device 2, which has a powerful power supply and correspondingly a relatively high transmission power, thus sends to the hearing aid component 1 a request in the form of a request to transmit desired data. The relatively high transmission power of the transmitter module 16 of the auxiliary device 2 guarantees that this request can be reliably identified by the hearing device component 1, even if the interference sources 8,9,10,13 in the hearing aid component 1 and the interference sources 17, 18, 19 in the Attachment 2 are unchanged in operation. Simultaneously with the request, the control units 6, 15 cause a change in the operating mode of the interference sources 8, 9, 10, 13, 17, 18, 19, in this case, a shutdown. During the transmission of the data from the hearing aid component 1 to the auxiliary device 2, all sources of interference 8, 9, 10, 13, 17, 18, 19 which are not directly for transmission or reception now remain both in the transmitting hearing device component 1 and in the receiving auxiliary device 2 The data needed for the duration of the transmission, so for example 50ms, disabled. The hearing aid component 1 responds exclusively to the request by the attachment 2 with the transmission of the requested data. In this way, an event-controlled change of the operating mode of the interference sources 8, 9, 10, 13, 17, 18, 19 ensures that interference is reduced during the transmission of data between the components 1, 2 of the hearing aid system.

Alternativ können dafür geeignete Störquellen statt einer Abschaltung auch kurzzeitig in einen Betriebszustand versetzt werden, der gegebenenfalls energetisch ungünstiger ist, also den Energieverbrauch der batteriebetriebenen Hörgerätekomponente 1 kurzzeitig erhöht, in dem die Störemissionen aber in einem für den Empfänger unkritischen Frequenzbereich liegen. Zusätzlich kann die Qualität der Kommunikationsverbindung dadurch verbessert werden, dass die Störquellen 8, 9, 10, 13, 17, 18, 19 auch dann in einen störarmen Betriebszustand versetzt werden, wenn das Zusatzgerät 2 Daten an die Hörgerätekomponente 1 übermittelt.Alternatively suitable sources of interference instead of a shutdown can also be briefly put into an operating state which is possibly less favorable in terms of energy, ie briefly increases the energy consumption of the battery-operated hearing aid component 1, but in which the spurious emissions lie in a frequency range which is uncritical for the receiver. In addition, the quality of the communication connection can be improved by the fact that the interference sources 8, 9, 10, 13, 17, 18, 19 are also placed in a low-noise operating condition when the auxiliary device 2 transmits data to the hearing aid component 1.

Es ist zur Umsetzung der Erfindung bereits ausreichend, während einer soeben beschriebenen Datenübertragung einzelne Störquellen, beispielsweise solche Störquellen, die besonders kritische Störungen in Form besonders schwer von Nutzsignalen zu unterscheidende Störsignale aussenden, in einen Betriebsmodus zu versetzen, in dem durch diese mindestens eine Störquelle eine gegenüber dem normalen Betriebsmodus zumindest abgeschwächte Einkopplung von Störsignalen in einen an der Datenübertragung beteiligten Empfänger erfolgt. Vorteilhafterweise werden jedoch alle identifizierten Störquellen in Reichweite der an der Datenübertragung beteiligten Empfänger in einen derartigen Betriebsmodus versetzt.It is already sufficient to implement the invention, during a data transfer just described individual sources of interference, such as interference sources that emit particularly critical interference in the form of particularly difficult to distinguish from useful signals noise to put in an operating mode in which at least one source of interference by a At least attenuated coupling of interference signals into a receiver participating in the data transmission takes place in comparison with the normal operating mode. Advantageously, however, all identified sources of interference within reach of the receivers involved in the data transmission are put into such an operating mode.

Fig. 2 zeigt ein Prinzipschaltbild eines binauralen Hörgerätesystems mit erfindungsgemäßer Datenübertragung. Ein derartiges binaurales Hörgerätesystem weist zwei separate Hörgerätekomponenten 1, 21 zur Schalldruckverstärkung auf, die jeweils an einem Ohr des Hörgeräteträgers angeordnet sind. Zwischen diesen Hörgerätekomponenten ist ebenfalls eine Kommunikation zum Datenaustausch erforderlich. Dies ergibt sich einerseits aus der Notwendigkeit eines Parameterabgleichs und verschiedenen Statusabfragen, die regelmäßig ausgeführt werden müssen, und andererseits aus physikalischen Gegebenheiten, die zur Realisierung bestimmter Hörgerätefunktionen das Zusammenwirken von mindestens zwei zueinander beabstandet angeordneten Mikrophonen erfordern. Die Kommunikation zwischen derartigen Hörgerätekomponenten muss dabei in der Regel in wesentlich kürzeren Zeitabständen erfolgen, als das beispielsweise zur Parametereinstellung durch externe Zusatzgeräte der Fall ist. Bei Vorliegen zweier unabhängiger Hörgerätekomponenten zur Schalldruckverstärkung sind diese jeweils mit einer separaten Energieversorgung ausgestattet, die in der Regel symmetrisch ausgelegt sein wird, d.h. jede der Hörgerätekomponenten verfügt nur über eine sehr kleine Batterie mit begrenzter Kapazität. In diesem Falle wäre es ungünstig, einer der Hörgerätekomponenten Kommunikationsaufgaben zuzuweisen, die mit einem gegenüber der anderen Hörgerätekomponente deutlich höheren Energieverbrauch verbunden sind, da das zur früheren Erschöpfung der Batterie in der jeweiligen Hörgerätekomponente führen würde und das der Aufgabe der Erfindung teilweise zuwider liefe. Fig. 2 shows a schematic diagram of a binaural hearing aid system with inventive data transmission. Such a binaural hearing aid system has two separate hearing device components 1, 21 for amplifying the sound pressure, which are each arranged on an ear of the hearing device wearer. Between these hearing aid components, a communication for data exchange is also required. This results, on the one hand, from the need for parameter adjustment and various status inquiries, which must be carried out regularly, and, on the other hand, from physical circumstances which, for the realization of certain hearing aid functions, arrange the interaction of at least two spaced-apart ones Require microphones. The communication between such hearing aid components usually has to take place at a much shorter time interval than is the case, for example, for setting parameters by means of external accessories. In the presence of two independent hearing aid components for sound pressure amplification, these are each equipped with a separate power supply, which will be designed symmetrically in the rule, ie each of the hearing aid components has only a very small battery with limited capacity. In this case, it would be unfavorable to assign communication tasks to one of the hearing aid components which are associated with a significantly higher energy consumption compared to the other hearing aid component, since this would lead to the earlier depletion of the battery in the respective hearing device component and would partially run counter to the object of the invention.

Aus diesem Grunde sind im vorliegenden binauralen Hörgerätesystem die Kommunikationsmittel in den einzelnen Hörgerätekomponenten symmetrisch ausgelegt, d.h. jede der beiden Hörgerätekomponenten 1, 21 verfügt über die gleichen Mittel zur Aufrechterhaltung bzw. Herstellung einer Kommunikationsverbindung zum Datenaustausch, und das zu ihrem Betrieb erforderliche Kommunikationsprotokoll ist ebenfalls symmetrisch ausgelegt. Jede der Hörgerätekomponenten 1, 21 verfügt über eine Spule 3, 23, die als Sender und Empfänger genutzt werden kann. Jede der Hörgerätekomponenten 1, 21 umfasst des weiteren eine Empfängerbaugruppe 5, 25, eine Steuereinheit 6, 26 sowie eine Senderbaugruppe 7, 27. Die Verknüpfung der einzelnen Baugruppen kann analog des vorangegangenen Ausführungsbeispiels vorgenommen werden. Die Steuereinheiten 6, 26 verfügen wiederum über Mittel, den jeweiligen Betriebsmodus einzelner identifizierter Störquellen 8, 28, 9, 29, 10, 30 zu verändern. Jede Hörgerätekomponente 1, 21 beinhaltet des weiteren je eine akustische Übertragungsstrecke mit einem Mikrophon 11, 31, einem Verstärker 12, 32 und einem Lautsprecher 13, 33 als schalldruckerzeugender Ausgabeeinheit.For this reason, in the present binaural hearing device system, the communication means in the individual hearing device components are designed symmetrically, ie each of the two hearing aid components 1, 21 has the same means for maintaining or establishing a communication connection for data exchange, and the communication protocol required for its operation is likewise symmetrical designed. Each of the hearing aid components 1, 21 has a coil 3, 23, which can be used as transmitter and receiver. Each of the hearing aid components 1, 21 further includes a receiver assembly 5, 25, a control unit 6, 26 and a transmitter assembly 7, 27. The linkage of the individual modules can be made analogous to the previous embodiment. The control units 6, 26 in turn have means to change the respective operating mode of individual identified sources of interference 8, 28, 9, 29, 10, 30. Each hearing aid component 1, 21 further includes an acoustic transmission path with a microphone 11, 31, an amplifier 12, 32 and a speaker 13, 33 as a sound pressure generating output unit.

Auch in derartigen Hörgerätesystemen ist es möglich, das Kommunikationsprotokoll so auszulegen, dass der Zeitpunkt, zu dem eine Spule 3, 23 in einer der Hörgerätekomponenten 1, 21 als Sender arbeitet, genau bekannt ist. Abweichend zum vorangegangenen Ausführungsbeispiel erfolgt diese Synchronisation jedoch nicht ereignisgesteuert durch ein Anfrage-Antwort-System, sondern zeitgesteuert. Zu diesem Zwecke verfügen die Steuereinheiten 6, 26 zusätzlich über Mittel zur Generierung einer Zeitinformation, beispielsweise über einen Timer-Schaltkreis 20, 40, der zumindest in regelmäßigen Abständen ein Zeitsignal an die Steuereinheit 6, 26 übermittelt. Bei entsprechender Synchronität dieser an die Steuereinheiten 6, 26 übermittelten Zeitsignale kann darauf aufbauend genau zeitgleich von den beiden Hörgerätekomponenten 1, 21 eine Kommunikationsverbindung zur Übertragung unterschiedlicher Daten hergestellt werden, wobei während der Dauer des Bestehens dieser Kommunikationsverbindung wiederum in erfindungsgemäßer Weise eine Änderung des Betriebsmodus bekannter Störquellen 8, 28, 9, 29, 10, 30 sowie 13, 33 erfolgt, wodurch sich diese Störquellen 8, 28, 9, 29, 10, 30, 13, 33 in einem Betriebsmodus befinden, in dem zumindest eine abgeschwächte Einkopplung von Störsignalen in den jeweils an der Datenübertragung beteiligten Empfänger erfolgt. Die Kommunikation zwischen den beiden Hörgerätekomponenten 1, 21 kann somit weitgehend frei von Störeinflüssen erfolgen, d.h. auch bei geringer Sendeleistung besteht eine hohe Übermittlungssicherheit der zu übertragenden Daten.Also in such hearing aid systems, it is possible to design the communication protocol so that the time at which a coil 3, 23 in one of the hearing aid components 1, 21 operates as a transmitter, is known exactly. Unlike the previous embodiment, however, this synchronization is not event-controlled by a request-response system, but time-controlled. For this purpose, the control units 6, 26 additionally have means for generating time information, for example via a timer circuit 20, 40, which transmits a time signal to the control unit 6, 26 at least at regular intervals. Given a corresponding synchronicity of these time signals transmitted to the control units 6, 26, a communication connection for transmitting different data can be established at precisely the same time by the two hearing aid components 1, 21, whereby a change of the operating mode is again known in the inventive manner during the duration of the existence of this communication connection Noise sources 8, 28, 9, 29, 10, 30 and 13, 33 takes place, as a result of which these interference sources 8, 28, 9, 29, 10, 30, 13, 33 are in an operating mode in which at least one attenuated coupling-in of interference signals takes place in each participating in the data transfer recipients. The communication between the two hearing aid components 1, 21 can thus be largely free from interference, i. even with low transmission power there is a high transmission reliability of the data to be transmitted.

Fig. 3 zeigt ein Prinzipschaltbild eines binauralen erfindungsgemäßen Hörgerätesystems mit einem zur Datenkommunikation geeigneten Zusatzgerät. Im Ausführungsbeispiel in Fig. 3 sind die Vorzüge der beiden bereits angeführten Ausführungsbeispiele vereint. Zum einen umfasst dieses Hörgerätesystem zwei separate Hörgerätekomponenten 1, 21, die jeweils an einem Ohr des Hörgeräteträgers angeordnet sind, und zum anderen umfasst das dargestellte Hörgerätesystem ein Zusatzgerät 2, das mit einer der Hörgerätekomponenten 21 eine Kommunikationsverbindung herstellen kann. Die Kommunikationsverbindung zwischen den beiden Hörgerätekomponenten 1, 21 wird zeitabhängig zyklisch hergestellt. Entsprechend zeitabhängig erfolgt eine Änderung des Betriebsmodus identifizierter Störquellen 8, 9, 10, 13, 28, 29, 30, 33. Die Kommunikation zwischen dem Zusatzgerät 2 und der Hörgerätekomponente 21 erfolgt ereignisgesteuert durch ein Anfrage-Antwort-System, wobei zumindest die Anfrage stets vom Zusatzgerät 2 ausgeht und mit wesentlich höherer Sendeleistung übermittelt wird. Entsprechend ereignisabhängig erfolgt durch die Anfrage die Änderung des Betriebsmodus der identifizierten Störquellen 17, 18, 19, 28, 29, 30, 33. Fig. 3 shows a schematic diagram of a binaural hearing aid system according to the invention with an appropriate for data communication additional device. In the embodiment in Fig. 3 the advantages of the two already mentioned embodiments are united. On the one hand, this hearing device system comprises two separate hearing device components 1, 21, which are each arranged on one ear of the hearing aid wearer, and on the other hand, the illustrated hearing aid system comprises an additional device 2, which can establish a communication connection with one of the hearing aid components 21. The communication connection between the two hearing aid components 1, 21 is cyclically produced time-dependent. A change of the operating mode of identified sources of interference 8, 9, 10, 13, 28, 29, 30, 33 takes place in a correspondingly time-dependent manner. The communication between the additional unit 2 and the hearing aid component 21 is event-controlled by a request-response system, whereby at least the request always occurs from the additional device 2 and transmitted with much higher transmission power. Depending on the event, the request changes the operating mode of the identified interference sources 17, 18, 19, 28, 29, 30, 33.

Die Initiierung einer Kommunikationsverbindung durch eine Anfrage, die mit hoher Sendeleistung übermittelt wird, ist immer dann sinnvoll, wenn die abfragende Komponente des Hörgerätesystems, vorliegend also das Zusatzgerät 2, über ausreichende Energiereserven verfügt und die Herstellung dieser Kommunikationsverbindung nicht regelmäßig und/oder sehr häufig erfolgen muss.The initiation of a communication connection by a request, which is transmitted with high transmission power, is always useful if the querying component of the hearing aid system, in this case the accessory 2, has sufficient energy reserves and the production of this communication connection is not made regularly and / or very often got to.

Die zeitabhängige Herstellung einer Kommunikationsverbindung mit zeitgleicher Veränderung des Betriebsmodus relevanter Störquellen ist immer dann sinnvoll, wenn die Herstellung dieser Kommunikationsverbindung sehr häufig und/oder regelmäßig erfolgen muss und die Aussendung eines relativ viel Energie verbrauchenden Anfragesignals den Energiehaushalt der kommunizierenden Hörgerätekomponenten 1, 21 zu stark belasten würde.The time-dependent production of a communication connection with simultaneous change of the operating mode relevant sources of interference is always useful when the production of this communication connection must be very frequent and / or regularly and the emission of a relatively much energy consuming request signal to the energy budget of the communicating hearing aid components 1, 21 too much burden would.

Im dargestellten Ausführungsbeispiel verfügt die Hörgerätekomponente 21 über eine zusätzliche Sende- und Empfangsspule 41, über die die Kommunikation mit dem Zusatzgerät 2 ablaufen kann. In einer alternativen nicht dargestellten Variante ist es jedoch auch möglich, die Kommunikation mit dem Zusatzgerät 2 und der anderen ohrnah getragenen Hörgerätekomponente 1 über ein und dieselbe Spule 23 zu realisieren. In einer weiteren nicht dargestellten Ausführungsform ist es außerdem möglich, beide ohrnahen Hörgerätekomponenten 1, 21 über Mittel zur Herstellung einer Kommunikationsverbindung mit einem externen Zusatzgerät 2 auszustatten, wodurch sich die Möglichkeit eines direkten Zugriffs derartiger Zusatzgeräte, beispielsweise von Fernbedienungen oder Programmiergeräten, auf die jeweilige Hörgerätekomponente 1, 21 ergibt. Dadurch können die Hörgerätekomponenten 1, 21 direkt an Bedürfnisse des Hörgeräteträgers angepasst werden, ohne dass eine Parameterübergabe über die zwischen den Hörgerätekomponenten 1, 21 bestehende Kommunikationsverbindung erfolgen muss.In the illustrated embodiment, the hearing aid component 21 has an additional transmitting and receiving coil 41, via which the communication with the auxiliary device 2 can proceed. In an alternative variant, not shown, however, it is also possible to realize the communication with the auxiliary device 2 and the other ear-worn hearing aid component 1 via one and the same coil 23. In another embodiment, not shown, it is also possible, both ear-near hearing aid components 1, 21 via means to provide a communication link with an external auxiliary device 2, which results in the possibility of direct access of such additional devices, such as remote controls or programming devices, to the respective hearing aid component 1, 21 results. As a result, the hearing device components 1, 21 can be adapted directly to the needs of the hearing device wearer without the need for a parameter transfer via the communication connection existing between the hearing aid components 1, 21.

Claims (21)

  1. Multi-component hearing aid system,
    comprising at least one first component (1) to be disposed on or in the ear of a patient for the purpose of generating and/or amplifying an auditory stimulus
    and at least one further component (2, 21) which engages at least partially and/or temporarily in a wireless inductive communication connection via which a data transmission can take place with the first component (1) to be worn on or in the ear, characterised in that
    circuitry means (6, 15, 26) are included which can place at least one source of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33) contained in the hearing aid system at least during the transmission of data into an operating mode in which interference signals are coupled by said at least one source of interference into a receiver (3, 4, 23, 41) involved in the data transmission in a manner which is at least attenuated compared to the normal operating mode,
    with the at least one source of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33) being a switching regulator, a display, a clocked switching circuit or a hearing device receiver contained in the hearing aid system.
  2. Hearing aid system according to claim 1, characterized in that circuitry means (6, 15) are included for effecting an event-driven change in the operating mode of at least one source of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33) during a transmission of data from one component of the hearing aid system to another component.
  3. Hearing aid system according to claim 1 or 2, characterized in that circuitry means (6, 20, 26, 40) are included for effecting a time-controlled change in the operating mode of at least one source of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33) during a transmission of data from one component of the hearing aid system to another component.
  4. Hearing aid system according to one of claims 1 to 3, characterized in that two components (1, 21) to be disposed on or in the ears of a patient for the purpose of generating and/or amplifying auditory stimuli are included which function as a binaural hearing aid system, wherein means (3, 23) for a wireless exchange of data between said components are included.
  5. Hearing aid system according to one of claims 1 to 4, characterized in that circuitry means (6, 15, 26) are included which can place a plurality of sources of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33) contained in the hearing aid system at least during the transmission of data between the components (1, 2, 21) of the hearing aid system into an operating mode in which interference signals are coupled by said sources of interference into receivers (3, 4, 23, 41) involved in the data transmission in a manner that is at least attenuated compared to the normal operating mode of the sources of interference.
  6. Hearing aid system according to one of claims 1 to 5, characterized in that the circuitry means (6, 15, 26) which can place the sources of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33) contained in the hearing aid system into a different operating mode during the transmission of data include means for deactivating the sources of interference.
  7. Hearing aid system according to claim 6, characterized in that circuitry means are included which compensate at least temporarily for the loss of function of a deactivated source of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33).
  8. Hearing aid system according to claim 7, characterized in that the circuitry means for compensating for the loss of function of a deactivated source of interference include capacitors.
  9. Hearing aid system according to one of claims 1 to 5, characterized in that the circuitry means (6, 15, 26) which can place the sources of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33) contained in the hearing aid system into a different operating mode during the transmission of data include means for varying the timing as clocked components acting as sources of interference and/or varying the power injected into the source of interference and/or otherwise influencing the interference spectrum.
  10. Hearing aid system according to one of claims 1 to 9, characterized in that at least one first component (1) to be disposed on or in the ear of a patient for the purpose of generating and/or amplifying an auditory stimulus and at least one further component (2) in the form of a remote control or a programming device, between which a wireless communication connection can be set up.
  11. Hearing aid component of a multi-component hearing aid system which can engage at least partially and/or temporarily in a wireless inductive communication connection with a further hearing aid component, characterized in that circuitry means (6, 15, 26) are included which at least during a transmission of data can place at least one source of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33) contained in the hearing aid component into an operating mode in which interference signals are coupled by said at least one source of interference into a receiver (3, 4, 23, 41) involved in the data transmission in a manner that is at least attenuated compared to the normal operating mode,
    with the at least one source of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33) being a switching regulator, a display, clocked switching circuit or a hearing device receiver contained in the hearing aid component.
  12. Hearing aid component according to claim 11, characterized in that circuitry means (6, 15) are included for effecting an event-driven change in the operating mode of at least one source of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33) during a transmission of data.
  13. Hearing aid component according to claim 11 or 12, characterized in that circuitry means (6, 20, 26, 40) are included for effecting a time-controlled change in the operating mode of at least one source of interference (8, 9, 10, 13, 17, 18, 19, 28, 29, 30, 33) during a transmission of data.
  14. Hearing aid component according to one of claims 11 to 13, characterized in that the hearing aid component is a hearing aid component (1) that is designed to be disposed on or in the ear of a patient for the purpose of generating and/or amplifying an auditory stimulus.
  15. Hearing aid component according to one of claims 11 to 13, characterized in that the hearing aid component is a remote control or a programming device of a multi-component hearing aid system.
  16. Method for operating a multi-component hearing aid system according to claim 1, between whose components a wireless data transmission can take place, characterized in that at least during the transmission of data between components of the hearing aid system at least one source of interference contained in the hearing aid system is placed into an operating mode in which interference signals are coupled by said at least one source of interference into a receiver involved in the data transmission in a manner that is at least attenuated compared to the normal operating mode,
    with the at least one source of interference being a switching regulator, a display, a clocked switching circuit or a hearing aid receiver contained in the hearing aid system.
  17. Method according to claim 16, characterized in that at least one source of interference contained in the hearing aid system is placed by a request for data transmission that is sent by a component of the hearing aid system in an event-driven manner during the transmission of data into an operating mode in which interference signals are coupled by said at least one source of interference into a receiver involved in the data transmission in a manner that is at least attenuated compared to the normal operating mode.
  18. Method according to claim 16 or 17, characterized in that at least one source of interference contained in the hearing aid system is placed in a time-controlled manner during the transmission of data into an operating mode in which interference signals are coupled by said at least one source of interference into a receiver involved in the data transmission in a manner that is at least attenuated compared to the normal operating mode.
  19. Method according to one of claims 16 to 18, characterized in that a plurality of sources of interference contained in the hearing aid system are placed during the transmission of data between the components of the hearing aid system into an operating mode in which interference signals are coupled by said sources of interference into receivers involved in the data transmission in a manner that is at least attenuated compared to the normal operating mode of the sources of interference.
  20. Method according to one of claims 16 to 19, characterized in that at least one source of interference contained in the hearing aid system is deactivated at least during the transmission of data.
  21. Method according to one of claims 16 to 19, characterized in that, by varying the timing and/or varying the power injected into the source of interference and/or otherwise influencing the interference spectrum, at least one source of interference contained in the hearing aid system is placed at least during the transmission of data into an operating mode in which interference signals are coupled by said source of interference into receivers involved in the data transmission in a manner that is at least attenuated compared to the normal operating mode of the source of interference.
EP08104397A 2007-07-02 2008-06-13 Multicomponent hearing aid system and a method for its operation Revoked EP2012509B1 (en)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102007030745A DE102007030745A1 (en) 2007-07-02 2007-07-02 Multi-component hearing aid system and a method for its operation

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EP2012509A1 EP2012509A1 (en) 2009-01-07
EP2012509B1 true EP2012509B1 (en) 2010-04-07

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EP08104397A Revoked EP2012509B1 (en) 2007-07-02 2008-06-13 Multicomponent hearing aid system and a method for its operation

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EP (1) EP2012509B1 (en)
JP (1) JP5021577B2 (en)
AT (1) ATE463935T1 (en)
AU (1) AU2008202727B2 (en)
DE (2) DE102007030745A1 (en)
DK (1) DK2012509T3 (en)

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DE102012217497A1 (en) 2012-09-26 2014-03-27 Airbus Operations Gmbh A method of detecting a noise generating device in an electrical network, an electrical system, and an aircraft

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AU2008202727B2 (en) 2010-07-22
JP2009017557A (en) 2009-01-22
DE502008000514D1 (en) 2010-05-20
ATE463935T1 (en) 2010-04-15
EP2012509A1 (en) 2009-01-07
DK2012509T3 (en) 2010-08-02
JP5021577B2 (en) 2012-09-12
AU2008202727A1 (en) 2009-01-22
DE102007030745A1 (en) 2009-01-08

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