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EP2034770B1 - Dispositif de transmission pour un dispositif auditif doté d'un blindage à conducteur plat - Google Patents

Dispositif de transmission pour un dispositif auditif doté d'un blindage à conducteur plat Download PDF

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Publication number
EP2034770B1
EP2034770B1 EP08105128A EP08105128A EP2034770B1 EP 2034770 B1 EP2034770 B1 EP 2034770B1 EP 08105128 A EP08105128 A EP 08105128A EP 08105128 A EP08105128 A EP 08105128A EP 2034770 B1 EP2034770 B1 EP 2034770B1
Authority
EP
European Patent Office
Prior art keywords
shielding
line
capacitance
wire
coil
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.)
Active
Application number
EP08105128A
Other languages
German (de)
English (en)
Other versions
EP2034770A2 (fr
EP2034770A3 (fr
Inventor
Peter Nikles
Gottfried Rückerl
Ulrich SCHÄTZLE
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
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Filing date
Publication date
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2034770A2 publication Critical patent/EP2034770A2/fr
Publication of EP2034770A3 publication Critical patent/EP2034770A3/fr
Application granted granted Critical
Publication of EP2034770B1 publication Critical patent/EP2034770B1/fr
Active 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; 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
    • H01—ELECTRIC ELEMENTS
    • H01Q—ANTENNAS, i.e. RADIO AERIALS
    • H01Q1/00—Details of, or arrangements associated with, antennas
    • H01Q1/27—Adaptation for use in or on movable bodies
    • H01Q1/273—Adaptation for carrying or wearing by persons or animals
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R1/00—Details of transducers, loudspeakers or microphones
    • H04R1/10—Earpieces; Attachments therefor ; Earphones; Monophonic headphones
    • 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
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/51—Aspects of antennas or their circuitry in or for hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2420/00—Details of connection covered by H04R, not provided for in its groups
    • H04R2420/07—Applications of wireless loudspeakers or wireless microphones

Definitions

  • the present invention relates to a transmission device for a hearing device with a resonant circuit including a capacitor and a coil and an electrical line in or to the resonant circuit, wherein the electrical line has a shield. Moreover, the present invention relates to an electrical coil with a wire winding to be screened. In particular, the present invention relates to a hearing device with such a coil for wirelessly receiving and / or transmitting signals.
  • hearing device is understood here to mean, in particular, a hearing device, but also any other device for sound output that can be worn on or in the ear, such as, for example, 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 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 for receiving the sound from the environment are installed.
  • 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
  • E-field influences are undesirable because they can be destructively superimposed with the useful signal from the magnetic field.
  • Affected by E-field couplings are the magnetic antennas (coil arrangements with and without ferrite core) and in particular their supply lines.
  • Conventional shields are for application in miniaturized hearing aids for space and effort reasons usually not applicable.
  • Patent US 4,926,007 A a shielded flexible foil conductor. This conductor can be used in particular for supply lines of antennas.
  • the document discloses DE 31 43 210 A1 an electrical component consisting of inductive and capacitive elements.
  • a wound into a plane, punched out of a metal foil trace structure is folded so that the superimposed conductor track parts form a continuous winding of the inductive element, while between selected, superimposed conductor track parts, a dielectric is arranged to form the capacitive element.
  • capacitive elements can be realized which together with the inductive element form a resonant circuit.
  • the object of the present invention is therefore to propose a transmission device for a hearing device with a shielded antenna feed, wherein the space is to be reduced.
  • a shielded antenna coil with reduced space requirement is to be provided.
  • an electrical coil can be used with a wire winding including a first and a second wire end, wherein the wire winding is formed single-layered in an axial direction starting at the first end of the wire and a wire section is guided at the second end of the wire against the axial direction as a shield directly over the wire winding ,
  • the shielding capacitance which is actually a parasitic capacitance
  • the use of the film conductor has the advantage that its capacity can be determined very accurately, whereby the necessary tolerances can be reduced. This in turn reduces the necessary tuning range and makes possible a so-called "on-chip tuning" in which on-chip tuning capacitors are switched on as required.
  • the tuning capacitor necessary for the resonant circuit of the transmission device can then be completely integrated into a semiconductor chip.
  • the coil of the resonant circuit has an own shield formed by its winding wire itself.
  • the intrinsic shielding is formed, as in the above-described electrical coil, by passing a wire end directly opposite the wire winding, in the direction opposite to the axial direction of the winding as shielding. In this way, voluminous shielding components can be avoided.
  • one of the signal lines and the shield line may be short-circuited at one end of the electrical line of the resonant circuit.
  • the shield is set to the potential of one end of the line and there is no special shielding potential to the electrical line to be performed.
  • the foil conductor can have a conductor layer, which can be interrupted laterally or laterally and thus used both for the signal line and for the shielding line.
  • the foil conductor may have a plurality of conductor layers for the signal line and the shield line.
  • FIG. 2 symbolically shows a part of a single-layer wound antenna coil 10.
  • the first coil end 11 represents the signal line input sig.
  • the second coil end 12, which is also used for shielding (see. FIG. 8 ) is applied to a screen or reference potential ref.
  • the two winding ends 11 and 12 are connected to a foil conductor 13.
  • the first winding end 11 with a signal line 14 of the film conductor 13 and the second Winding end 12 connected to a shield line 15. It is therefore shown here the case that the antenna is connected with a connection to a reference potential (ground or supply voltage) and for this connection, a shield layer or the shield line 15 of the film conductor 13 is used.
  • a reference potential ground or supply voltage
  • FIG. 3 is a section III / III through the film conductor 13 of FIG. 2 shown. Accordingly, located on a carrier film 16, a conductor layer which is interrupted laterally or laterally twice. This results in three lines: In the middle of the signal line 14 and left and right of the shield lines 15, which are connected to each other at the end of the film conductor 13.
  • FIG. 4 an alternative foil conductor 13 is shown. He has on the one flat side as the film conductor of FIG. 3 a longitudinally extending signal line 14. On the other flat side of the carrier film 16 (in FIG. 4 the underside) is also a metal coating which is used as the shielding line 17. Between the signal line 14 and the shield line 17 so here is the carrier film 16th
  • FIG. 5 Another embodiment of a foil conductor with shielding is in FIG. 5 played.
  • This construction represents a combination of the ladder constructions of the FIGS. 3 and 4
  • the signal line 14 and the shield line 15 are arranged, while on the bottom of the additional shielding line 17 is arranged.
  • FIG. 6 is a development of the film conductor 13 of FIG. 5 shown.
  • a further carrier film 16 'and in turn another additional shielding 17' arranged.
  • FIG. 3 So a two - layered structure (carrier and conductor layer) of Foil conductor 13 shows, put the FIGS. 4 and 5 a three-layer construction and FIG. 6 a five-layer structure of the film conductor 13.
  • FIGS. 4 and 5 By such a multilayer film conductor 13 with integrated shielding, so can be a space-saving lead for an inductive antenna realize.
  • the shielding of the supply line is of crucial importance for the construction of critical hearing aids with magnetic data transmission.
  • the choice of the supply line length and the way of laying the supply line must be set much less strict. This is particularly important for in-the-ear hearing aids with individually manufactured housing shells.
  • parallel resonant circuits with high quality are used, which have a high receiving sensitivity and a high frequency selectivity because of the voltage overshoot in the vicinity of the resonance. Due to the shielding one gains an increased signal-to-noise ratio and a suppression of interfering signals that are not directly in the vicinity of the operating frequency.
  • the nature of the lead shielding affects particularly antennas that are part of a parallel resonant circuit.
  • the construction-related and usually not negligible supply capacity can be part of the resonant circuit capacity.
  • the capacitance is very well defined and the dielectric losses very low.
  • the capacity of the shield can therefore be used as a full part of the useful capacity. Due to the clear definition of the shield capacitance, parallel resonant circuits of high quality can be developed. This is very difficult with twisted lines, which are commonly used in hearing aids, since their capacity and shielding capacity vary greatly. Consequently, in the known hearing aids a relatively high tuning range in terms of capacity is necessary.
  • FIG. 7 shows a multi-layer wound coil 10 'with the coil ends 11 and 12 on one side of the coil 10'.
  • An inner winding layer 18 is wound around a cylindrical ferrite core 20 in a first axial direction 19.
  • An outer winding layer 21, however, is wound in a first axial direction 19 opposite second axial direction 22 to the underlying windings.
  • the wire end 12 of the outer winding layer 21 is connected to the reference potential ref.
  • FIG. 8 symbolically shows a longitudinal section through a single-coil antenna coil 10.
  • the wire winding with its two winding ends 11 and 12 is wound in the first axial direction 19 via the ferrite core 20.
  • a part of the winding wire in front of the second end 12 serves as a return wire 23.
  • This return wire is guided or wound in the opposite second axial direction 22 over the winding layer and subsequently connected to the reference potential ref.
  • the degree of feedback 23 is therefore at reference potential and makes the underlying winding position insensitive to acting E-fields.
  • Such coils are also very suitable for higher frequency operating frequencies up to 20 MHz.
  • FIG. 9 shows a circuit diagram of a transmission device according to the invention.
  • a resonant circuit consisting of the antenna coil 10 or L res with a main resonant capacitor C res is fed by a chip 24, which in turn is connected to ground GND and is supplied by a supply voltage V +.
  • the chip 24 provides the signal potentials Sig + and Sig-.
  • the potential Sig + is fed via the signal line 14 of the film conductor 13 directly to the coil 10.
  • the other potential Sig- is also applied to the coil 10 via the signal line 14 of a foil conductor 13.
  • This wiring diagram of the coil 10 represents an equivalent circuit diagram for the coils of FIGS. 7 and 8 represents.
  • the shield lines 15 of the film conductors 13 are connected to a specific reference potential V ref , which is also provided by the chip 24.
  • This reference potential V ref is independent of the signal potentials Sig + and Sig-, resulting in a balanced wiring of the inductive antenna.
  • the shielding of the foil conductor 13 leads to an additional capacitance C guard .
  • This because of the nature of the film conductor very defined shielding capacitance C guard is parallel to the capacitance C res , so that the resonant circuit capacitance is roughly formed from the sum of the capacitances C res plus C guard .
  • the entire resonant circuit capacity is to be tuned exactly, which is why parallel to the main capacitor C res on the chip 24 tuning capacitances are provided, which are symbolized in the circuit diagram by the variable capacitance C chip . Since the manufacturing tolerances of the foil conductor are low, especially with regard to the shielding, only a small tuning range is required with regard to the resonant circuit capacitance. This can be realized by the capacitors or the variable capacitance C chip on the chip 24.
  • FIG. 10 a further embodiment of the transfer device according to the invention is shown. While with the circuit of FIG. 9 a symmetrical wiring of the inductive antenna 10, namely with the signal potentials Sig + and Sig- is possible by the circuit of FIG. 10 realized an asymmetrical wiring of the inductive antenna 10.
  • the one terminal of the coil 10 is placed here via the signal line 14 to reference potential V ref .
  • the other terminal of the coil 10 is connected to a signal potential Sig which, like the reference potential V ref, is provided by a chip 24 '.
  • the parallel resonant circuit C res , L res is therefore at the two potentials V ref and Sig.
  • the shield line 15 is short-circuited to the signal line 14.
  • the antenna Despite shielding, the antenna then has only two instead of three connections (cf. FIGS. 7 and 8 ). This is particularly important for miniaturization, since then only two of the relatively large connection pads must be maintained. In order to avoid current loops, it is also advantageously provided that the shielding layer or the shielding line 15 is connected to the reference potential terminal V ref on only one side of the foil conductor 13.

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  • Engineering & Computer Science (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Physics & Mathematics (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Health & Medical Sciences (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Near-Field Transmission Systems (AREA)
  • Coils Or Transformers For Communication (AREA)
  • Decoration By Transfer Pictures (AREA)
  • Cable Transmission Systems, Equalization Of Radio And Reduction Of Echo (AREA)
  • Shielding Devices Or Components To Electric Or Magnetic Fields (AREA)

Claims (6)

  1. Dispositif de transmission pour une prothèse auditive, comprenant
    - un circuit oscillant incluant un condensateur ( Cres ) et une bobine ( Lres, 10 ) ainsi que
    - une ligne électrique dans le circuit oscillant ou y allant,
    caractérisé en ce que
    - la ligne électrique comporte un blindage,
    - la ligne électrique comporte un conducteur ( 13 ) en feuille ayant une ligne ( 14 ) de signal et une ligne ( 15 ) de blindage, dont l'armature de condensateur est définie et dont la capacité ( Cguard ) de blindage est montée en parallèle au condensateur, et la capacité de blindage ensemble avec la capacité du condensateur ( Cres ) est utilisée à dessein comme capacité du circuit oscillant,
    - au condensateur ( Cres ) est raccordé un condensateur ( Cchip ) d'accord variable et intégré complètement dans une puce à semiconducteur.
  2. Dispositif de transmission suivant la revendication 1, dans lequel la bobine ( Lres, 10 ) comporte un blindage propre formé par son fil d'enroulement soi-même.
  3. Dispositif de transmission suivant la revendication 2, dans lequel la bobine ( Lres, 10 ) comporte un enroulement de fil incluant une première extrémité ( 11 ) et une deuxième extrémité ( 12 ) de fil et dans lequel l'enroulement de fil est formé en une seule couche dans une direction ( 19 ) axiale en commençant à la première extrémité ( 11 ) de fil et une section ( 23 ) de fil à la deuxième extrémité ( 12 ) de fil passe dans le sens opposé au sens ( 22 ) axial en tant que blindage directement sur l'enroulement de fil.
  4. Dispositif de transmission suivant l'une des revendications précédentes, dans lequel la ligne ( 14 ) de signal et la ligne ( 15 ) de blindage sont court-circuitées à une extrémité de la ligne électrique.
  5. Dispositif de transmission suivant l'une des revendications précédentes, dans lequel le conducteur ( 13 ) en feuille comporte une couche conductrice, qui est interrompue latéralement et qui est utilisée ainsi à la fois pour la ligne ( 14 ) de signal et pour la ligne ( 15 ) de blindage.
  6. Dispositif de transmission suivant l'une des revendications précédentes, dans lequel le conducteur ( 13 ) en feuille comporte plusieurs couches conductrices pour la ligne ( 14 ) de signal et pour la ligne ( 15 ) de blindage.
EP08105128A 2007-09-07 2008-08-26 Dispositif de transmission pour un dispositif auditif doté d'un blindage à conducteur plat Active EP2034770B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102007042592A DE102007042592A1 (de) 2007-09-07 2007-09-07 Übertragungseinrichtung für eine Hörvorrichtung mit Folienleiterschirmung und eigengeschirmte Spule

Publications (3)

Publication Number Publication Date
EP2034770A2 EP2034770A2 (fr) 2009-03-11
EP2034770A3 EP2034770A3 (fr) 2009-03-18
EP2034770B1 true EP2034770B1 (fr) 2012-02-29

Family

ID=39892371

Family Applications (1)

Application Number Title Priority Date Filing Date
EP08105128A Active EP2034770B1 (fr) 2007-09-07 2008-08-26 Dispositif de transmission pour un dispositif auditif doté d'un blindage à conducteur plat

Country Status (5)

Country Link
US (1) US8379898B2 (fr)
EP (1) EP2034770B1 (fr)
AT (1) ATE547902T1 (fr)
DE (1) DE102007042592A1 (fr)
DK (1) DK2034770T3 (fr)

Families Citing this family (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE69941603D1 (de) 1998-10-05 2009-12-10 Cognis Ip Man Gmbh Cytochrom P450 Monooxygenase Gen und Protein des omega-Hydroxylase-Komplexes von Candida tropicalis und darauf bezogene Verfahren
US8259975B2 (en) 2008-09-03 2012-09-04 Siemens Medical Instruments Pte. Ltd. Hearing aid with an attenuation element
DE102008045668B4 (de) * 2008-09-03 2012-04-19 Siemens Medical Instruments Pte. Ltd. Hörhilfe mit Dämpfungselement
DE102014203169A1 (de) * 2014-02-21 2015-09-10 Siemens Medical Instruments Pte. Ltd. Antenne mit Schirmvorrichtung und Herstellungsverfahren
EP3110175B1 (fr) 2015-06-24 2020-03-25 Oticon A/s Dispositif auditif comprenant une unité d'antenne encastrée dans tiroir de batterie
WO2019097495A1 (fr) * 2017-11-20 2019-05-23 Cochlear Limited Fabrication de réseau d'électrodes
TWI773940B (zh) * 2019-11-12 2022-08-11 美律實業股份有限公司 無線耳機

Family Cites Families (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3143210A1 (de) 1981-10-30 1983-05-11 Max-E. Dipl.-Ing. 7320 Göppingen Reeb "elektrisches bauteil"
US4926007A (en) * 1989-03-03 1990-05-15 W. H. Brady Co. Shielded flexible connector and process therefor
US6694034B2 (en) * 2000-01-07 2004-02-17 Etymotic Research, Inc. Transmission detection and switch system for hearing improvement applications
AUPR520301A0 (en) * 2001-05-23 2001-06-14 Cochlear Limited Transceiver coil for auditory prosthesis
AU2003242912B2 (en) * 2002-05-31 2008-10-16 Med-El Elektromedizinische Geraete Gmbh Low power signal transmission
EP1416635B1 (fr) * 2002-11-01 2012-12-12 Omron Corporation Dispositif capteur
US6940466B2 (en) 2003-11-25 2005-09-06 Starkey Laboratories, Inc. Enhanced magnetic field communication system
US7615856B2 (en) * 2004-09-01 2009-11-10 Sanyo Electric Co., Ltd. Integrated antenna type circuit apparatus

Also Published As

Publication number Publication date
EP2034770A2 (fr) 2009-03-11
EP2034770A3 (fr) 2009-03-18
US20090067649A1 (en) 2009-03-12
US8379898B2 (en) 2013-02-19
DE102007042592A1 (de) 2009-03-26
ATE547902T1 (de) 2012-03-15
DK2034770T3 (da) 2012-06-18

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