EP2389015A2 - Prothèse auditive avec unité passive placée au fond du conduit auditif - Google Patents

Prothèse auditive avec unité passive placée au fond du conduit auditif Download PDF

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Publication number
EP2389015A2
EP2389015A2 EP11163877A EP11163877A EP2389015A2 EP 2389015 A2 EP2389015 A2 EP 2389015A2 EP 11163877 A EP11163877 A EP 11163877A EP 11163877 A EP11163877 A EP 11163877A EP 2389015 A2 EP2389015 A2 EP 2389015A2
Authority
EP
European Patent Office
Prior art keywords
unit
hearing
ear canal
housing
hearing aid
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP11163877A
Other languages
German (de)
English (en)
Inventor
Frank Beck
Frank Naumann
Uwe Rass
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
Original Assignee
Siemens Medical Instruments Pte Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2389015A2 publication Critical patent/EP2389015A2/fr
Withdrawn legal-status Critical Current

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; 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
    • H04R25/65—Housing parts, e.g. shells, tips or moulds, or their manufacture
    • 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
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/023—Completely in the canal [CIC] hearing aids

Definitions

  • the present invention relates to a hearing device with a unit which is completely insertable into a human auditory canal and which has a housing in which a sound receiving element, a receiver and an amplifier connected in between are integrated.
  • a hearing device here means any sound-emitting device that can be worn in or on the ear, in particular a hearing device, a headset, headphones and the like.
  • Hearing aids are portable hearing aids that are used to care for the hearing impaired.
  • different types of hearing aids such as behind-the-ear hearing aids (BTE), hearing aid with external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (IDO), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
  • BTE behind-the-ear hearing aids
  • RIC hearing aid with external receiver
  • IDO in-the-ear hearing aids
  • ITE canal hearing aids
  • the hearing aids listed by way of example are worn on the outer ear or in the ear canal.
  • bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
  • Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is usually integrated in a signal processing unit. This basic structure is in FIG. 1 shown using the example of a behind-the-ear hearing aid. In a hearing aid housing 1 for Carrying behind the ear, one or more microphones 2 are installed for recording the sound from the environment.
  • a signal processing unit 3 which is also integrated in the hearing aid housing 1, processes the microphone signals and amplifies them.
  • the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal.
  • the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
  • the power supply of the hearing device and in particular the signal processing unit 3 is effected by a likewise integrated into the hearing aid housing 1 battery. 5
  • IdO hearing aids or CIC hearing aids are preferably placed deep in the ear canal or ear canal near the eardrum.
  • the reasons for this are on the one hand that the wearing of the hearing aid should not be visible, and on the other hand that a better sound quality can be achieved if the volume between the earpiece and the eardrum is small.
  • a hearing aid with all its components has a certain minimum volume and should still fit in a small ear canal.
  • the individual size of the ear canal varies significantly. It is not possible to use a hearing aid deeply in every ear canal today (deep-fit). The larger the hearing device or the hearing device, the less it is suitable for a deep seat in the ear canal; all the less so with small auditory canals.
  • a hearing aid in which the processor unit is located outside the ear canal.
  • the processor unit is connected by a cable to the deep seated in the ear canal part.
  • the pamphlets reveal WO 04010734 and US 6724902 a seal deep in the ear canal, with the signal processing components sitting in the external ear canal. A Connection between both units is ensured by a sound tube.
  • a hearing device with a first, in the ear canal portable component having a receiving unit for receiving wireless signals known. It also has a structurally separate from the first component, second component, which is also portable in the ear canal and has a transmitting unit for wireless transmission of signals and / or energy to the receiving unit of the first component.
  • the first component can be designed batteryless.
  • the second component located farther out in the ear canal, can be easily removed from the ear canal for battery replacement.
  • the object of the present invention is to provide a hearing device which is more likely to be used in a smaller ear canal.
  • the passive, physically independent part of the hearing device makes this smaller in relation to the prior art, since a separate energy source in the part of the hearing device is not necessary.
  • the part of the hearing thus smaller can be trained, he can be used deeper in an ear canal.
  • the sound receiving element is designed as a silicon microphone.
  • silicon microphones are robust and very small executable.
  • the second unit i. H. the unit for wireless power consumption, also designed for wireless data transmission.
  • the wireless transmission serves several purposes.
  • the second unit can be designed so that it receives commands from the outside wirelessly and the received commands are executable by the first unit. This allows a deeply inserted into the ear canal part of a hearing device can be controlled wirelessly from the outside. Specifically, it may be convenient to form the second unit for receiving fitting parameters wirelessly for the first unit.
  • the hearing device has a third unit physically separate from the first and second units, which is portable in or on the outer ear and which is adapted for wireless radiation of energy to the second unit.
  • This third unit is easily accessible from the outside, so that, for example, a removal from the ear for charging or a battery exchange without great effort and in particular without removing the seated deep in the ear canal part of a hearing aid is possible.
  • the energy delivering third unit may also be worn at another body site.
  • the third unit may have a processor, wherein bidirectional data exchange is enabled between the first unit and the third unit via the second unit, so that raw data from the first unit in the third unit can be processed and the processed data is transferable back to the first unit.
  • the deep seated in the ear canal part of the hearing can be made even smaller.
  • the part of the hearing device sitting deep in the auditory canal then requires less energy that has to be transmitted via the wireless interface.
  • the second unit may comprise an annular antenna with an air-core coil. This can be used coaxially in the ear canal and can also serve as a holding element for the first unit.
  • the second unit has an encapsulation with a handle portion with which the second and first unit can be pulled out of the human auditory canal.
  • FIG. 2 shows as a hearing device according to the invention a two-part hearing aid in a schematic view. Below the schematic view is a cross section through a human The auditory canal is shown in or on which realized components of this hearing aid are placed.
  • FIG. 2 a first unit 11, which has the actual signal processing components of a hearing aid.
  • a second unit 12 is electrically connected, which is designed for wireless power consumption and power to the first unit 11.
  • the second unit 12 receives the power from a third unit 13 that is physically separate from the second unit 12.
  • the first unit 11 has a housing 14.
  • a sound receiving element here a microphone 15 (in particular a silicon microphone) housed.
  • the signal of the microphone 15 is fed to an amplifier unit 16, which also has a processor. With the processor in the usual way, the gain is adjustable and special filtering can be performed.
  • the output signal of the amplifier unit 16 is fed to a loudspeaker or receiver 17, which converts the processed and amplified signal into sound.
  • the first unit 11 has no own energy source and in particular no own battery. It is thus designed purely passive. Nevertheless, a power supply of the first unit 11 is necessary. This energy supply takes place here indirectly through the second unit 12, which is physically affiliated to the first unit 11.
  • the second unit 12 has an electromagnetic coupling element with which energy can be obtained from an electromagnetic field.
  • the second unit 12 has a coil 18 which is designed for inductive energy absorption.
  • the second unit 12 can also be equipped with an antenna with which electromagnetic energy can be absorbed.
  • the second unit 12 has an enclosure 20 which is mechanically coupled to the housing 14 of the first unit 11.
  • the encapsulation 20 may be a housing, a simple jacket or a potting compound surrounding the coil 18 and the lines 19.
  • the third unit 13 which is physically separate from the second unit 12, provides the energy necessary for the first unit 11.
  • the third unit 13 has, for example, a in FIG. 2 not shown battery, so that the third unit can also be referred to as a battery module.
  • the third unit 13 has an inverter, which in FIG. 2 simplified as oscillator 21 is shown.
  • the inverter including the non-illustrated battery is housed here in a housing 22 of the third unit. From the housing 22, a coil 23 is led out, which is connected by means of lines 24 to the oscillator 21.
  • the coil and the lines are in turn surrounded by an encapsulation 25 for insulation and protection purposes.
  • This encapsulation 25 may again be a housing, a simple jacket or a potting compound.
  • the third unit 13 generates with its coil 23 for the purpose of coupling 26 an alternating magnetic field which induces a corresponding alternating voltage in the coil 18 of the second unit 12. From the induced voltage, the energy required for the first unit 11 can be obtained.
  • the two coils 18 and 23 are as efficient as possible inductive coupling aligned.
  • the energy transfer can also be effected by an electric field (capacitive transmission) or by any other electromagnetic fields.
  • FIG. 2 In the lower section of FIG. 2 is shown a cross section through the ear canal of a human ear.
  • the hearing aid shown schematically in the figure above is positioned in the auditory canal 27 or the auricle 28.
  • the individual units 11, 12 and 13 or their encapsulations 20, 25 or housing 14 have possible realistic shapes.
  • the first unit 11 is inserted very deep into the ear canal 27 and is located immediately in front of the eardrum 29.
  • the shape of the housing 14 of the first unit 11 is adapted to the shape of the ear canal 27 in the desired portion.
  • the second unit 12 Immediately following the first unit 11 is in the direction of the output of the ear canal 27, the second unit 12.
  • the encapsulation 20 of the second unit 12 does not close the ear canal 27, so that sound through the ear canal 27 to the microphone 15 of the first unit 11th can get into the housing 14.
  • stabilizing elements can be used.
  • the first unit 11 with its housing 14 can contribute to this, because the encapsulation 20 is mechanically coupled to the housing 14.
  • the third unit 13 may be worn behind the pinna 28 or in the pinna or on the pinna.
  • the housing 22 including the enclosure 25 has a hook-like shape and is hooked into the concha 30.
  • the housing 22 then projects downwards between anti-helix and anti-tragus. It can be seen that the two encapsulations 20 and 25 are directly opposite, so that a good inductive coupling between the respective coils 18 and 23 is ensured.
  • FIG. 3 shows an alternative embodiment of a hearing device according to the invention.
  • the structure of this hearing device essentially corresponds to that of FIG. 2 , so that with regard to the individual components and reference numerals to the description of FIG. 2 is referenced.
  • the difference in both embodiments, however, is that the hearing device or the hearing aid of FIG. 3 has an external processor 31 and is capable of bidirectional data exchange.
  • the amplifier unit 16 has here except the actual amplifier (AMP) no actual processor, but a data transmission device (TRANS).
  • the processor 31 of the hearing device is integrated into the third unit 13 which is arranged outside the auditory canal, for which reason it is also referred to as an external processor.
  • the third unit 13 also has a transmission device 32 (TRANS).
  • This transmitter 32 has a bidirectional connection to the processor 31 (PROC) in the housing 22.
  • the transmitter 32 is as in the example of FIG. 2 designed to invert the DC voltage of the battery, not shown, so that as in the example of FIG. 2 Energy from the third unit 13 to the second unit 12 and first unit 11 can be transmitted.
  • the deep in the Ear canal fitted part of the hearing ie, the units 11 and 12 are designed completely passive. So you have no battery or other energy source.
  • this part has only a microphone, an amplifier, and a built-in handset with an earpiece, earmold, or dome for comfortable carrying.
  • the passive part is placed deep in the ear canal, outside the ear canal there is an energy store, namely the third unit 13, and both parts are wirelessly connected by an electromagnetic field.
  • the advantages of this design are, on the one hand, that the part inserted deep into the ear canal can be built much smaller.
  • the externally worn part of the hearing aid including the battery can be made less conspicuous, z. B. as a flat part behind the ear or with a jewel-like housing. It is also advantageous that the outer part can be easily loaded or replaced as needed.
  • the encapsulation of the antenna in particular of an air coil, is designed annular.
  • a ferrite core coil can be used.
  • the antenna enclosure 20 can also be provided with an extension or tension element to the inner part of the hearing aid, d. H. to pull the first unit 11 with the second unit 12 from the ear canal 27.
  • the outer part of the hearing device, d. H. the third unit 13 can be placed anywhere on the pinna with the condition that the two coils 23, 18 of the outer part and the inner part are aligned with each other for maximum coupling.
  • the coil type of the outer part 13 may be arbitrary.
  • a ferrite coil or an air coil can also be used here.
  • the encapsulation of the coil 23 may also be annular or cylindrical, and the coil may be visibly supported in the auricle 28 or behind the pinna.
  • ferrite materials or other magnetically active materials can be used to shape the magnetic field for better magnetic coupling.

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  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Manufacturing & Machinery (AREA)
  • Circuit For Audible Band Transducer (AREA)
EP11163877A 2010-05-21 2011-04-27 Prothèse auditive avec unité passive placée au fond du conduit auditif Withdrawn EP2389015A2 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102010021173A DE102010021173A1 (de) 2010-05-21 2010-05-21 Hörvorrichtung mit passiver, tief im Gehörgang sitzender Einheit

Publications (1)

Publication Number Publication Date
EP2389015A2 true EP2389015A2 (fr) 2011-11-23

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EP11163877A Withdrawn EP2389015A2 (fr) 2010-05-21 2011-04-27 Prothèse auditive avec unité passive placée au fond du conduit auditif

Country Status (3)

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US (1) US20110286616A1 (fr)
EP (1) EP2389015A2 (fr)
DE (1) DE102010021173A1 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106341766A (zh) * 2015-07-08 2017-01-18 奥迪康有限公司 分隔件和包括分隔件的听力装置

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US8363872B2 (en) * 2009-04-14 2013-01-29 Dan Wiggins Magnetic earpiece coupling
US8340335B1 (en) * 2009-08-18 2012-12-25 iHear Medical, Inc. Hearing device with semipermanent canal receiver module
EP2595413B1 (fr) * 2011-11-17 2015-07-01 Oticon A/S Fixage d'appareils auditifs
KR102007509B1 (ko) 2013-05-06 2019-08-06 삼성전자주식회사 고막과 청각 장치간의 거리를 측정하는 청각 장치 및 방법
WO2016025826A1 (fr) 2014-08-15 2016-02-18 iHear Medical, Inc. Dispositif auditif intracanal et procédés pour la télécommande sans fil d'un appareil
US9769577B2 (en) 2014-08-22 2017-09-19 iHear Medical, Inc. Hearing device and methods for wireless remote control of an appliance
US20160134742A1 (en) 2014-11-11 2016-05-12 iHear Medical, Inc. Subscription-based wireless service for a canal hearing device
WO2020028085A1 (fr) 2018-07-31 2020-02-06 Earlens Corporation Évent d'embout d'auriculaire dans un système auditif de contact
EP3614694B1 (fr) 2018-08-20 2023-12-20 GN Hearing A/S Système d'écoute binaurale ayant des moyen de communication sans fil en champ proche
DK3657818T3 (da) 2018-11-26 2023-07-03 Gn Hearing As Trådløst nærfeltsmagnetinduktionskommunikationssystem med dynamisk ændring af transmissionseffekt
US11864915B2 (en) * 2020-03-26 2024-01-09 Starkey Laboratories, Inc. Ear-worn electronic system employing wireless powering arrangement for powering an in-ear component during sleep

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WO2004010734A1 (fr) 2002-07-18 2004-01-29 Insound Medical, Inc. Dispositif auditif intracanal a insert tubulaire
US6724902B1 (en) 1999-04-29 2004-04-20 Insound Medical, Inc. Canal hearing device with tubular insert
DE102006024411A1 (de) 2006-05-24 2007-11-29 Siemens Audiologische Technik Gmbh Verfahren zum Erzeugen eines Schallsignals oder zum Übertragen von Energie in einem Gehörgang und entsprechende Hörvorrichtung
WO2008010716A2 (fr) 2006-07-21 2008-01-24 Exsilent Research B.V. Prothèse auditive, module d'extension et procédé de fabrication d'une prothèse auditive

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DE19837913C2 (de) * 1998-08-20 2000-09-28 Implex Hear Tech Ag Implantierbare Vorrichtung mit einer eine Empfangsspule aufweisenden Ladestromeinspeiseanordnung
JP2003521337A (ja) * 2000-01-31 2003-07-15 メド−エル・エレクトロメディツィニシェ・ゲラーテ・ゲーエムベーハー 外耳に部分的に挿入可能な移植蝸牛システム
DE10343292B3 (de) * 2003-09-18 2004-12-02 Siemens Audiologische Technik Gmbh Hörgerät ohne separates Mikrofongehäuse
US7256747B2 (en) * 2004-01-30 2007-08-14 Starkey Laboratories, Inc. Method and apparatus for a wireless hearing aid antenna
US20060233412A1 (en) * 2005-04-14 2006-10-19 Siemens Audiologische Technik Gmbh Microphone apparatus for a hearing aid
DK2582158T3 (en) * 2005-06-05 2016-11-28 Starkey Labs Inc Communication system for wireless audio devices
JP2009141793A (ja) * 2007-12-07 2009-06-25 Yukihiro Ando 電気音響変換器

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6724902B1 (en) 1999-04-29 2004-04-20 Insound Medical, Inc. Canal hearing device with tubular insert
WO2004010734A1 (fr) 2002-07-18 2004-01-29 Insound Medical, Inc. Dispositif auditif intracanal a insert tubulaire
DE102006024411A1 (de) 2006-05-24 2007-11-29 Siemens Audiologische Technik Gmbh Verfahren zum Erzeugen eines Schallsignals oder zum Übertragen von Energie in einem Gehörgang und entsprechende Hörvorrichtung
WO2008010716A2 (fr) 2006-07-21 2008-01-24 Exsilent Research B.V. Prothèse auditive, module d'extension et procédé de fabrication d'une prothèse auditive

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106341766A (zh) * 2015-07-08 2017-01-18 奥迪康有限公司 分隔件和包括分隔件的听力装置
CN106341766B (zh) * 2015-07-08 2020-09-22 奥迪康有限公司 分隔件和包括分隔件的听力装置

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US20110286616A1 (en) 2011-11-24
DE102010021173A1 (de) 2011-11-24

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