EP1983800B1 - Hörvorrichtung mit störarmer höreransteuerung und entsprechendes verfahren - Google Patents
Hörvorrichtung mit störarmer höreransteuerung und entsprechendes verfahren Download PDFInfo
- Publication number
- EP1983800B1 EP1983800B1 EP08103047.0A EP08103047A EP1983800B1 EP 1983800 B1 EP1983800 B1 EP 1983800B1 EP 08103047 A EP08103047 A EP 08103047A EP 1983800 B1 EP1983800 B1 EP 1983800B1
- Authority
- EP
- European Patent Office
- Prior art keywords
- hearing
- data transmission
- frequency
- frequency band
- transmission
- 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
Links
- 238000000034 method Methods 0.000 title claims description 10
- 230000005540 biological transmission Effects 0.000 claims description 52
- 238000001228 spectrum Methods 0.000 claims description 13
- 230000002457 bidirectional effect Effects 0.000 claims description 5
- 238000007493 shaping process Methods 0.000 description 5
- 230000036039 immunity Effects 0.000 description 4
- 230000008901 benefit Effects 0.000 description 3
- 230000006870 function Effects 0.000 description 3
- 230000005236 sound signal Effects 0.000 description 3
- 210000000988 bone and bone Anatomy 0.000 description 2
- 210000000613 ear canal Anatomy 0.000 description 2
- 230000001939 inductive effect Effects 0.000 description 2
- 208000032041 Hearing impaired Diseases 0.000 description 1
- 230000003321 amplification Effects 0.000 description 1
- 230000008033 biological extinction Effects 0.000 description 1
- 230000007423 decrease Effects 0.000 description 1
- 210000000883 ear external Anatomy 0.000 description 1
- 230000002349 favourable effect Effects 0.000 description 1
- 238000001914 filtration Methods 0.000 description 1
- 210000003128 head Anatomy 0.000 description 1
- 230000006872 improvement Effects 0.000 description 1
- 230000006698 induction Effects 0.000 description 1
- 230000002452 interceptive effect Effects 0.000 description 1
- 238000003199 nucleic acid amplification method Methods 0.000 description 1
- 230000008569 process Effects 0.000 description 1
- 230000033764 rhythmic process Effects 0.000 description 1
- 230000000638 stimulation Effects 0.000 description 1
- 210000003454 tympanic membrane Anatomy 0.000 description 1
Images
Classifications
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- 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
- H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
- H04R25/353—Frequency, e.g. frequency shift or compression
-
- 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
- H04R25/554—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
Definitions
- the present invention relates to a hearing device with a transmission unit for wireless data transmission in a main frequency band, a loudspeaker and a drive device for driving the loudspeaker with a drive signal. Moreover, the present invention relates to a corresponding method for operating a hearing device.
- hearing device is understood here in particular a hearing aid, a headset, headphones and other portable devices on the head.
- 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) and in-the-ear hearing aids (IDO), e.g. also Concha hearing aids or canal hearing aids (CIC), provided.
- BTE behind-the-ear hearing aids
- IDO in-the-ear hearing aids
- CIC 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 of the signal processing unit 3 is carried out by a likewise integrated into the hearing aid housing 1 battery. 5
- PDM pulse density modulation
- PWM pulse width modulation
- the digital control has the advantage that in digital hearing aids, the level of the digital-to-analog converter can be omitted.
- Digital drive circuits also have a significantly higher efficiency than analog drive circuits.
- analog drive circuits are less noisy, i. they prove a limited to the acoustic signal frequency spectrum with a low harmonic content.
- the high levels of harmonic distortion associated with digital control interfere with wireless transmission of data between hearing aids and transmission between a hearing aid and external accessories (remote control, wireless programmer, wireless relay, etc.).
- the document discloses US 2004/0109577 A1 a hearing aid device with a clock generator.
- the clock signal is considered within a time frame of a few minutes as a stable signal with a constant period and pulse width.
- the frequency of the clock generator is changed.
- the object of the present invention is thus to enable a power-saving digital control of the loudspeaker of the hearing device especially for digitally operating hearing devices.
- a corresponding method for operating a hearing device is to be provided.
- this object is achieved by a hearing device according to claim 1.
- the invention provides a method according to claim 6.
- the drive signal of the drive device is pulse density modulated. This makes it possible to control a low-pass inductive loudspeaker without a high signal processing effort of a digital signal processing circuit.
- the data transmission by the transmission device can be broadband in a plurality of frequency bands, and the frequency spectrum of the drive signal can each have a significant incision in the region of each of the frequency bands.
- the inventive principle can also be used for a broadband transmission of high data rate.
- the transmission device can have a bandpass filter which essentially allows only frequency components which lie in the main frequency band or in the main frequency band and in the range of many of them to pass. As a result, the interference immunity of the wireless transmission can be additionally increased.
- the hearing device according to the invention can be configured in a special embodiment as in-the-ear hearing aid, even if the power consumption and the space available there are extremely limited. Because of the small amount of space available, the handset, which is usually a magnetoacoustic transducer, is very close to the receiver coil. In addition, with in-the-ear hearing aids, the position and orientation of each device is unique. In any case, the listener induces more or less large interference in the receiver coil. As a result, the signal-to-noise ratio is generally significantly worsened there. The poor signal-to-noise ratio could be improved by an increased transmission power, but this can only be achieved by an enormous energy demand. Therefore, the solution according to the invention is all the more welcome to spectrally separate the drive signal for the listener from the transmission signal for wireless data transmission.
- a hearing system with two hearing aids is provided according to the invention, each having the structure of the hearing device described above, the transmission facilities of both hearing aids allow bidirectional, wireless data transmission, and a data transmission in one direction in another frequency band than a data transmission in the other direction.
- the transmission facilities of both hearing aids allow bidirectional, wireless data transmission, and a data transmission in one direction in another frequency band than a data transmission in the other direction.
- FIG. 2 is a hearing aid system with two hearing aids 10 and 11 shown schematically.
- the two hearing aids 10, 11 have the same structure. For clarity, however, only in the hearing aid 10, the essential components for the present invention are shown.
- the central unit of the ITE hearing aid 10 is a signal processing or control unit 12. It is powered by a battery 13. Its output signal is used to control a receiver 14, which is usually designed as a magnetoacoustic transducer.
- the control unit 12 also controls a transmission unit 15, which serves here for bidirectional transmission to the second hearing device 11.
- the transmission device 15 is symbolized by a coil, but it may also contain other transmission components.
- FIG. 2 It can be seen that the electronic components are arranged in the ITE hearing aid 10 spatially very close to each other.
- the handset 14 and the transmission unit 15 are placed very close together, so that there is an involuntary mutual interference and interference.
- FIG. 3 shows a typical PDM drive signal with which the drive unit 12 timed the handset 14.
- the information to be transmitted to the listener is in the pulse density.
- FIG. 4 a section of this signal is reproduced in an enlarged view. The density of the pulses varies in the desired manner.
- the handset 14 has a specific inductive characteristic. Therefore, the leads in FIG. 3 reproduced time PDM voltage signal in the listener to that in the FIG. 3 Dashed line current waveform.
- the frequency spectrum of the PDM voltage signal of FIG. 3 is in FIG. 5 shown. It consists essentially of arcs that are periodically lined up and whose amplitude decreases due to the rectangular shape of the PDM pulses according to the function sin x / x. In certain areas of the spectrum, namely between two arcs, incisions E are produced in the spectrum, ie so-called "vacated areas". In these vacated areas so no or hardly any interference occurs. There then only the useful signal N or Nutzsignalanmaschine N 'are present. The emergence of the incisions E, which are also referred to as "notches" can be explained as follows: The pulse durations Tp of the PDM signal are fixed and occur in a fixed time grid of nx Tp.
- the basic idea of the present invention is now to adapt the operating frequency of the digital receiver control to the wireless transmission system. Specifically, therefore, it is attempted to remove interfering receiver noise components from the used frequency band for wireless data transmission. This is achieved here by the appropriate favorable shaping of the interference spectrum ("noise-shaping") by the operating frequency of the PDM modulator is just chosen so that the incisions E are in the range of transmission frequency for the wireless transmission or their multiples. Thus, the wireless transmission is only slightly affected and the benefits of digital handset control remain.
- noise components from the frequency ranges used for the wireless data transmission can be supplemented by further known "noise-shaping" methods.
- noise components from the low-frequency range of the audio signals can be pushed in a known manner in the direction of higher frequencies.
- the width and the shape of the incisions can be optimized in each case or "notches".
- the immunity to interference of the wireless transmission against the handset control can be further improved by performing the signal processing of the wireless transmission part with a band-pass filter that only allows frequencies within the wireless bandwidth to pass unhindered.
- the filter function F of such a bandpass filter is in FIG. 6 represented together with the PDM frequency spectrum of the example signal.
- the improvement of immunity to interference is particularly effective if the characteristics of the bandpass filter (slope of the filter edges, quality of the filter) and the characteristic of the "noise-shaping" are adapted to each other.
- notches In the example of FIG. 5 occur at fixed frequency intervals "notches". In the simplest case, only one of them is used for wireless data transmission. However, for high-bandwidth applications, wireless transmission may be split into multiple sub-frequency ranges. Then the sub-frequency ranges should be in the other "notches" of the PDM drive signal to the listener. With regard to the immunity to disturbance, the characteristics of the bandpass and of the "noise-shaping" should also be adapted to each other. This can be achieved, for example, with special comb filters whose passband are matched to the "notches".
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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)
- Circuit For Audible Band Transducer (AREA)
- Transceivers (AREA)
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE200710018121 DE102007018121B4 (de) | 2007-04-16 | 2007-04-16 | Hörvorrichtung mit störarmer Höreransteuerung und entsprechendes Verfahren sowie Hörsystem |
Publications (3)
Publication Number | Publication Date |
---|---|
EP1983800A2 EP1983800A2 (de) | 2008-10-22 |
EP1983800A3 EP1983800A3 (de) | 2009-10-28 |
EP1983800B1 true EP1983800B1 (de) | 2016-12-14 |
Family
ID=39535305
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP08103047.0A Active EP1983800B1 (de) | 2007-04-16 | 2008-03-28 | Hörvorrichtung mit störarmer höreransteuerung und entsprechendes verfahren |
Country Status (6)
Country | Link |
---|---|
EP (1) | EP1983800B1 (da) |
JP (1) | JP5322485B2 (da) |
CN (1) | CN101312602B (da) |
AU (1) | AU2008201690B2 (da) |
DE (1) | DE102007018121B4 (da) |
DK (1) | DK1983800T3 (da) |
Families Citing this family (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
AU2010225449A1 (en) * | 2009-03-16 | 2011-10-13 | Cochlear Limited | Transcutaneous modulated power link for a medical implant |
DE102010039303A1 (de) * | 2010-08-13 | 2012-02-16 | Siemens Medical Instruments Pte. Ltd. | Verfahren zum Reduzieren von Interferenzen und Hörvorrichtung |
DE102021200642B3 (de) | 2021-01-25 | 2022-03-17 | Sivantos Pte. Ltd. | Hörgerät |
CN113081765B (zh) * | 2021-04-15 | 2022-06-07 | 四川千里倍益康医疗科技股份有限公司 | 电动按摩器及其基于pwm的骨骼识别方法 |
WO2024004925A1 (ja) * | 2022-06-28 | 2024-01-04 | ピクシーダストテクノロジーズ株式会社 | 信号処理装置、マイク付きイヤホン、信号処理方法、およびプログラム |
Family Cites Families (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CA2212131A1 (en) * | 1996-08-07 | 1998-02-07 | Beltone Electronics Corporation | Digital hearing aid system |
JP2904272B2 (ja) * | 1996-12-10 | 1999-06-14 | 日本電気株式会社 | ディジタル補聴器、及びその補聴処理方法 |
US6605991B2 (en) * | 2001-08-30 | 2003-08-12 | Motorola, Inc. | Circuitry for creating a spectral null in a differential output switching amplifier and method therefor |
DE10245556B3 (de) | 2002-09-30 | 2004-04-22 | Siemens Audiologische Technik Gmbh | Hörhilfegerät oder Hörgerätesystem mit einem Taktgenerator und Verfahren zu deren Betrieb |
DE10304648B3 (de) * | 2003-02-05 | 2004-08-19 | Siemens Audiologische Technik Gmbh | Vorrichtung und Verfahren zur Kommunikation von Hörgeräten |
US7289568B2 (en) * | 2003-11-19 | 2007-10-30 | Intel Corporation | Spectrum management apparatus, method, and system |
CN101015000A (zh) * | 2004-06-28 | 2007-08-08 | 皇家飞利浦电子股份有限公司 | 无线音频 |
US7529378B2 (en) * | 2004-11-12 | 2009-05-05 | Phonak Ag | Filter for interfering signals in hearing devices |
CN101124849B (zh) * | 2005-01-17 | 2012-07-04 | 唯听助听器公司 | 用于操作助听器的装置和方法 |
JP2006217088A (ja) * | 2005-02-01 | 2006-08-17 | Sharp Corp | 聴覚伝送システム |
DK1860914T3 (da) * | 2006-05-24 | 2009-03-30 | Phonak Ag | System til hörehjælp og fremgangsmåde til drift af dette |
-
2007
- 2007-04-16 DE DE200710018121 patent/DE102007018121B4/de active Active
-
2008
- 2008-03-28 DK DK08103047.0T patent/DK1983800T3/da active
- 2008-03-28 EP EP08103047.0A patent/EP1983800B1/de active Active
- 2008-04-15 JP JP2008105561A patent/JP5322485B2/ja active Active
- 2008-04-16 CN CN2008101314532A patent/CN101312602B/zh active Active
- 2008-04-16 AU AU2008201690A patent/AU2008201690B2/en not_active Ceased
Non-Patent Citations (1)
Title |
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None * |
Also Published As
Publication number | Publication date |
---|---|
CN101312602A (zh) | 2008-11-26 |
CN101312602B (zh) | 2012-04-25 |
JP5322485B2 (ja) | 2013-10-23 |
DE102007018121A1 (de) | 2008-10-30 |
EP1983800A3 (de) | 2009-10-28 |
AU2008201690A1 (en) | 2008-10-30 |
EP1983800A2 (de) | 2008-10-22 |
DK1983800T3 (da) | 2017-03-27 |
DE102007018121B4 (de) | 2012-12-06 |
AU2008201690B2 (en) | 2010-01-28 |
JP2008271549A (ja) | 2008-11-06 |
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