EP1915030A1 - Appareil auditif doté d'une boucle en métal conducteur de courant - Google Patents

Appareil auditif doté d'une boucle en métal conducteur de courant Download PDF

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Publication number
EP1915030A1
EP1915030A1 EP07117731A EP07117731A EP1915030A1 EP 1915030 A1 EP1915030 A1 EP 1915030A1 EP 07117731 A EP07117731 A EP 07117731A EP 07117731 A EP07117731 A EP 07117731A EP 1915030 A1 EP1915030 A1 EP 1915030A1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
electrical conductor
antenna
supply unit
faceplate
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.)
Granted
Application number
EP07117731A
Other languages
German (de)
English (en)
Other versions
EP1915030B1 (fr
Inventor
Volker Gebhardt
Peter Nikles
Erika Radick
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos GmbH
Original Assignee
Siemens Audiologische Technik GmbH
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
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Application filed by Siemens Audiologische Technik GmbH filed Critical Siemens Audiologische Technik GmbH
Publication of EP1915030A1 publication Critical patent/EP1915030A1/fr
Application granted granted Critical
Publication of EP1915030B1 publication Critical patent/EP1915030B1/fr
Revoked legal-status Critical Current
Anticipated expiration legal-status Critical

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/65—Housing parts, e.g. shells, tips or moulds, or their manufacture
    • H04R25/652—Ear tips; Ear moulds
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/025—In the ear hearing aids [ITE] hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/49—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

Definitions

  • the present invention relates to a hearing aid with an antenna for receiving and / or transmitting inductive signals, a signal processing device to which the antenna is connected, a power supply unit for powering the signal processing device and an electrical conductor for electrically connecting the power supply unit with the signal processing device.
  • antenna for receiving and / or transmitting inductive signals
  • signal processing device to which the antenna is connected
  • power supply unit for powering the signal processing device
  • electrical conductor for electrically connecting the power supply unit with the signal processing device.
  • 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), in-the-ear hearing aids (IDO) and Concha hearing aids are provided.
  • BTE behind-the-ear hearing aids
  • IDO in-the-ear hearing aids
  • Concha hearing aids are provided.
  • 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 shown in FIG 1 using the example of a behind-the-ear hearing aid. In a hearing aid housing 1 for carrying behind the ear are one or more microphones 2 to Built-in sound recording 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 of the signal processing unit 3 is carried out by a likewise integrated into the hearing aid housing 1 battery. 5
  • Electromagnetic interferences generated within the hearing aid burden the receiving path of the transmission system, so that only those external signals can be received whose signal strength is above the signal strength of the interference signals.
  • Typical sources of electromagnetic interference are, for example, the handset, which is designed as a magnetic transducer, or the hearing aid electronics, which itself emits electromagnetic interference signals.
  • all connecting lines between the components of the hearing aid, which act as inductive antennas by the flow of current through these lines as sources of interference are mentioned.
  • the receiving antenna or a receiving coil of a wireless signal transmission system which uses the inductive range or the typical RF range, the superposition of these numerous, emanating from the different noise sources electromagnetic interference signals is received.
  • a corresponding hearing aid with a line loop to compensate for inductive interference is from the patent DE 10 2004 051 226 B3 known. Specifically, there is proposed to lay a line loop so that its axis is parallel to that of a transmitting / receiving coil.
  • the compensation of inductive interference fields has the disadvantage that the size of the interference fields must be known, at least on the order of magnitude.
  • Another disadvantage of this cable routing is that the line when closing the hearing aid can be clamped, chipped or bent. In addition, this cable routing requires sufficient space, for example, around the battery of the hearing aid.
  • the antennas are mounted in a hearing aid so that they touch a battery of the hearing aid as large as possible.
  • the battery shields the antenna from electromagnetic radiation emanating from other components of the hearing aid, for example from the loudspeaker.
  • the object of the present invention is to keep the effect of interference fields in hearing aids with simple means low.
  • a hearing aid with an antenna for receiving and / or transmitting inductive signals, a signal processing device to which the antenna is connected, a power supply unit for powering the signal processing device and an electrical conductor for electrically connecting the power supply unit with the signal processing device, said the electrical conductor is L- or U-shaped nestled to the power supply unit and the electrical conductor forms part of a round or rectangular ring whose axis has a main direction component perpendicular to the longitudinal axis of the antenna.
  • an interference field of a current-carrying electrical conductor is minimized in that it is aligned so that its interference field is aligned perpendicular to the maximum sensitivity of susceptible components of the hearing aid.
  • the interference between interference field and effective field are thereby minimized and not intentionally sought as in the case of compensation.
  • the hearing aid can be designed as in-the-ear hearing aid with a faceplate, wherein the longitudinal axis of the antenna is arranged perpendicular to the faceplate, and a leg of the electrical conductor is also formed perpendicular to the faceplate.
  • the electrical conductor is essentially made of a metal band. This can be arranged to save space compared to a round conductor with the same cable cross-section at the given orientation.
  • the power supply unit has a circular-cylindrical battery, it is favorable to allow the electrical conductor to run partially in the radial direction and partially in the axial direction of the battery. As a result, a short electrical conductor can be realized, which runs around the battery.
  • the electrical conductor may be welded to a battery contact.
  • the electrical conductor may also be part of a battery contact. In the latter case, a partial reduction results in an advantageous manner.
  • the invention is based on the finding that the spatial orientation of a receiving coil moves within certain angular limits. This is due to the fact that on the one hand the function of a radio transmission must be ensured and on the other hand, the available space in the ear canal is physiognomically limited.
  • the interference of the magnetic field with the receiving antenna depends on the amplitude and direction of the magnetic field with respect to the orientation of the receiving antenna.
  • lines can now be geometrically guided such that coupling of the magnetic field into the receiving antenna is minimized becomes.
  • the interference of the magnetic field on a receiving coil can be kept as small as possible by this measure not only locally, but over a larger spatial area.
  • transmitter and receiver coils are to be arranged parallel to each other.
  • the antennas or coils are therefore within certain limits, due to the orientation of the auditory canal, to align perpendicular to the faceplate level. If, as is usually the case, leads are guided in in-the-ear hearing aids in the faceplate level, these lines span a current loop and generate a magnetic field which is oriented predominantly parallel to the receiving antenna. This would result in a maximum Störfeldeinkopplung.
  • FIG 2 is a faceplate 10 again, which is equipped with a battery 11 and a printed circuit board 12.
  • the axis of the battery 11 is parallel to the faceplate plane, d. H.
  • a metal bracket 13 serves to direct the current from the battery 11 to the circuit board 12. It is rigid and consists of a band-shaped conductor material. He is not carried out here isolated because he touches no electronic components other than the one pole of the battery 11th
  • the metal bracket is L-shaped.
  • One of its legs 131 extends from the axis of the battery in the radial direction of the battery and is perpendicular to the faceplate plane.
  • the other leg 132 of the metal bracket 13 extends along the lateral surface of the battery 11 along its axial direction.
  • the first leg 131 is integral with a Battery contact 133 connected and held in a special section of the faceplate 10.
  • the second leg 132 is connected at its free end to the circuit board 12, which is not apparent in FIG.
  • the metal bracket 13 thus forms part of a substantially rectangular ring whose axis is parallel to the faceplate plane. AC components in this metal bracket 13 thus lead to a magnetic field with a main component parallel to the faceplate level.
  • a receiving antenna as mentioned above, is usually arranged almost perpendicular to the faceplate 10, d. H. its main directional component is perpendicular to the faceplate plane, the magnetic interference field caused by the metal strap 13 is substantially perpendicular to the receiving antenna. As a result, the interference field is minimized.
  • the metal bracket is a sturdy component and is welded to the battery contact or is part of the battery terminal 133 itself, the structural tolerance to laying loose wire lines is reduced.
  • the clearly defined position of the metal bracket is essential for the function of the transmission system.
  • the location of the receiving coil can be varied within the hearing aid, since the interference was minimized over a larger spatial area according to the invention.
  • a construction technique of hearing aids in which the receiving antenna is independent can be implemented by the other components.
  • the solution according to the invention furthermore eliminates the expense of additional line loops, which generally generate a counter field only locally. Furthermore, due to the greater freedom with respect to the spatial placement of the receiving antenna, it is possible to construct smaller in-the-ear hearing aids.

Landscapes

  • Engineering & Computer Science (AREA)
  • Manufacturing & Machinery (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Support Of Aerials (AREA)
EP07117731A 2006-10-16 2007-10-02 Appareil auditif doté d'une boucle en métal conducteur de courant Revoked EP1915030B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102006049469A DE102006049469B4 (de) 2006-10-16 2006-10-16 Hörgerät mit stromführendem Metallbügel

Publications (2)

Publication Number Publication Date
EP1915030A1 true EP1915030A1 (fr) 2008-04-23
EP1915030B1 EP1915030B1 (fr) 2012-06-27

Family

ID=38938284

Family Applications (1)

Application Number Title Priority Date Filing Date
EP07117731A Revoked EP1915030B1 (fr) 2006-10-16 2007-10-02 Appareil auditif doté d'une boucle en métal conducteur de courant

Country Status (4)

Country Link
EP (1) EP1915030B1 (fr)
CN (1) CN101166376B (fr)
DE (1) DE102006049469B4 (fr)
DK (1) DK1915030T3 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102009007233A1 (de) * 2009-02-03 2010-08-12 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung mit Störkompensation und Entwurfsverfahren

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102018207179B4 (de) * 2018-05-08 2020-03-19 Sivantos Pte. Ltd. Hörhilfegerät mit Elektronikrahmen und darin integrierter Antenne

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5020136A (en) * 1986-04-21 1991-05-28 Motorola, Inc. Battery pack antenna suitable for use with two-way portable transceivers
EP1583395A2 (fr) * 2004-03-31 2005-10-05 Siemens Audiologische Technik GmbH Prothèse auditive intra-auriculaire pour le traitement binaural d'un patient
EP1587343A2 (fr) * 2004-04-13 2005-10-19 Siemens Audiologische Technik GmbH Prothèse auditive
DE102004051226B3 (de) * 2004-10-20 2006-01-19 Siemens Audiologische Technik Gmbh Hörhilfegerät mit einer Leitungsschleife zur Kompensation induktiver Störfelder

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6639564B2 (en) * 2002-02-13 2003-10-28 Gregory F. Johnson Device and method of use for reducing hearing aid RF interference
ATE508590T1 (de) * 2004-02-19 2011-05-15 Oticon As Hörgerät mit antenne zum empfangen und senden elektromagnetischer signale und abshirmende batterie

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5020136A (en) * 1986-04-21 1991-05-28 Motorola, Inc. Battery pack antenna suitable for use with two-way portable transceivers
EP1583395A2 (fr) * 2004-03-31 2005-10-05 Siemens Audiologische Technik GmbH Prothèse auditive intra-auriculaire pour le traitement binaural d'un patient
EP1587343A2 (fr) * 2004-04-13 2005-10-19 Siemens Audiologische Technik GmbH Prothèse auditive
DE102004051226B3 (de) * 2004-10-20 2006-01-19 Siemens Audiologische Technik Gmbh Hörhilfegerät mit einer Leitungsschleife zur Kompensation induktiver Störfelder

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102009007233A1 (de) * 2009-02-03 2010-08-12 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung mit Störkompensation und Entwurfsverfahren
DE102009007233B4 (de) * 2009-02-03 2012-07-26 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung mit Störkompensation und Entwurfsverfahren
US8396235B2 (en) 2009-02-03 2013-03-12 Siemens Medical Instruments Pte. Ltd. Hearing aid with interference compensation and method for configurating the hearing aid

Also Published As

Publication number Publication date
DE102006049469B4 (de) 2010-04-15
EP1915030B1 (fr) 2012-06-27
CN101166376B (zh) 2011-07-06
CN101166376A (zh) 2008-04-23
DE102006049469A1 (de) 2008-04-24
DK1915030T3 (da) 2012-09-24

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