EP1274278A2 - Procédé d'utilisation d'une prothèse auditive et une prothèse auditive numérique programmable correspondante - Google Patents

Procédé d'utilisation d'une prothèse auditive et une prothèse auditive numérique programmable correspondante Download PDF

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Publication number
EP1274278A2
EP1274278A2 EP02013818A EP02013818A EP1274278A2 EP 1274278 A2 EP1274278 A2 EP 1274278A2 EP 02013818 A EP02013818 A EP 02013818A EP 02013818 A EP02013818 A EP 02013818A EP 1274278 A2 EP1274278 A2 EP 1274278A2
Authority
EP
European Patent Office
Prior art keywords
gain
frequency
hearing aid
audio signal
amplification
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
EP02013818A
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German (de)
English (en)
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EP1274278A3 (fr
EP1274278B1 (fr
Inventor
Hervé Schulz
Tom Weidner
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
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Application filed by Siemens Audiologische Technik GmbH filed Critical Siemens Audiologische Technik GmbH
Publication of EP1274278A2 publication Critical patent/EP1274278A2/fr
Publication of EP1274278A3 publication Critical patent/EP1274278A3/fr
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Publication of EP1274278B1 publication Critical patent/EP1274278B1/fr
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    • 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
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically
    • 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
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing

Definitions

  • the invention relates to a method for operating a digital programmable hearing aid with an input converter for recording an input signal and converting it into an audio signal, a signal processing unit for processing and frequency-dependent amplification of the audio signal and one Output transducer.
  • the invention further relates to a digital one programmable hearing aid for performing the method.
  • the whistle typical for feedback is usually proportionate high frequencies.
  • They are hearing aids with one volume control that can be actuated by the hearing aid wearer, e.g. the hearing aid model "Swing" from Siemens Audiologischetechnik GmbH, through which the reinforcement of a Audio signal can be changed.
  • the Raising or lowering the gain of the audio signal in Dependence on the frequency, being at a low Gain almost the entire transmission range of the Hearing aid is equally reinforced and at a high Amplification higher frequencies are amplified less than lower frequencies.
  • the frequency-dependent gain according to the volume control is static.
  • EP 0 250 679 B1 describes a hearing aid with a Storage means for storing coefficients related a filter frequency response known.
  • the object of the present invention is to provide a method for Operation of a hearing aid and a hearing aid specify that allow a wide frequency response.
  • This task is done in a method of operating a digital programmable hearing aid with at least one input converter for recording an input signal and conversion into an audio signal, a signal processing unit for processing and frequency-dependent amplification of the audio signal and an output converter solved in that a transmission characteristic a maximum amplification of the audio signal is adjustable over the frequency and at least in one Frequency range from an adjustable by the hearing aid wearer Parameters and / or one of the signal processing unit automatically generated parameters at least one gain change value is determined, with the respective Frequency taking into account a gain output value of the gain change value is a final gain value is determined and this to the maximum gain is limited so that effective system reinforcement results for the respective frequency.
  • the part relating to a digital programmable hearing aid The object is achieved in that the hearing aid at least has a memory for recording gain values to identify a maximum transmission characteristic Amplification of the audio signal over frequency.
  • the hearing aid according to the invention is, for example around a hearing aid worn behind the ear, an in hearing aid that can be worn in the ear, an implantable hearing aid or a pocket hearing aid. Furthermore, the hearing aid according to the Invention also part of several devices for supplying one Comprehensive hearing aid system, e.g. part a hearing aid system with two hearing aids worn on the head for binaural care or part of a hearing aid system, consisting of a device that can be worn on the head and one on the body portable processor unit.
  • the hearing aid includes one Input converter for receiving an input signal. Usually serves as an input converter a microphone, which is an acoustic Record signal and into an electrical audio signal converts.
  • the hearing aid according to the invention further comprises a signal processing unit for processing and frequency-dependent amplification of the audio signal.
  • the Signal processing in the hearing aid takes place by means of a digital one Signal processor (DSP), the way it works by means of programs or parameters which can be influenced in the hearing aid is.
  • DSP digital one Signal processor
  • This allows the operation of the signal processing unit the individual's hearing loss Hearing aid wearer as well as the current hearing situation in which adjust the hearing aid. That changed
  • the audio signal is fed to an output converter. This is usually designed as a listener who converts electrical audio signal into an acoustic signal.
  • other embodiments are also possible here, e.g. an implantable output transducer that works directly with an ossicle is connected and this stimulates vibrations.
  • an audio signal in the narrower Understood an electrical signal that originates from the signal received by the input converter and from is transmitted to the hearing aid. It usually contains in the audible Frequency range information.
  • the audio signal can be used in signal processing in the hearing aid in analog or are in digital form, with the hearing aid in the signal path both signal forms can also occur simultaneously.
  • an audio signal also understood an electrical signal, which from the audio signal in the narrower sense results from further processing, for example through filtering, transformation, etc.
  • the invention provides that a transmission characteristic of a maximum amplification of the audio signal over frequency adjustable, i.e. for example when fitting the hearing aid is freely configurable by the acoustician.
  • Farther at least one amplification output value is stored in the hearing aid, which is preferably also adjustable by the acoustician is.
  • the gain output value can be for the entire transferable frequency range of the hearing aid or constant within each frequency band of the hearing aid his. However, it is advantageous (within certain Limits) any gain output value for each frequency adjustable so that a transmission characteristic of a normal amplification of the audio signal over frequency is freely configurable.
  • the normal gain When setting the normal gain, it is determined by what factor an input audio signal with a certain Signal amplitude amplified depending on the frequency becomes. Instructs the hearing aid through the hearing aid wearer operated volume control, it is located to set the normal gain preferably in a middle position so that the hearing aid wearer has the opportunity has, the gain, based on this basic setting, increase or decrease equally.
  • the Setting the normal gain and the maximum gain can include both hearing aid specific as well as aspects relating to the individual hearing aid wearer respectively. For example, when adjusting of a hearing aid to a user found that at a certain frequency and a certain gain Feedback whistle occurs, so the maximum Gain in this frequency range below this gain set.
  • the transmission characteristics are for a certain frequency range and for a certain value range of the gain preferably freely configurable.
  • the Transfer characteristics using suitable adaptation software set as such and transferred to the hearing aid but you can also just specify a few Frequency and gain value pairs can be set. Further is not only a continuous course but also a discontinuous one Course of the transmission characteristics possible.
  • the actual amplification of an audio signal in a hearing aid is in addition to the frequency of a number of others Factors dependent. Such factors can arise from the current Adjustment of the volume control on the hearing aid, the Amplitude of the input signal or from a signal analysis in parameters derived from the signal processing unit of the hearing aid his. The latter are done, for example, by algorithms for situation analysis, for noise reduction or for automatic gain control ( AGC) determined. Generally speaking, with modern hearing aids a number of control functions influence the instant reinforcement.
  • the gain output value is now under Consideration of all factors influencing the reinforcement (Gain change values) at the respective frequency of the Gain end value determined. Exceeds the gain limit the preset maximum at the respective frequency Gain, so this is at the maximum gain limited. The effective system reinforcement is therefore always less than or equal to the maximum gain.
  • the invention offers the advantage that it allows for a specific Hearing aid almost any normal gain as well as set almost any maximum gain can be.
  • the signal processing in the hearing aid can thereby both to hearing aid-specific conditions and to the individual hearing loss of a hearing aid wearer better to adjust.
  • the invention also has the advantage that that multiple influencing factors that affect the Act on amplification (e.g. current position of the volume control, Gain change through a signal processing algorithm, set maximum gain) better be taken into account.
  • An embodiment of the invention provides that the signal processing in several parallel frequency channels
  • Signal processing unit and the transmission characteristic the normal amplification of the audio signal over frequency and / or the transmission characteristic of the maximum gain of the audio signal versus frequency for each Channel can be set separately.
  • the division of the audible Frequency range in several channels makes adaptation easier a hearing aid if a certain channel (i.e. parameters relating to a specific frequency range) this channel can be regarded as constant.
  • Figure 5 shows a multi-channel hearing aid with an overall roll-off logic.
  • FIG. 1 shows the circuit implementation of a Roll-offs for a hearing aid with analog signal processing.
  • the amplifier circuit comprises an operational amplifier OA, which has an input resistor R1 and a RC element consisting of a potentiometer R2 and a capacitor C is connected in the feedback branch.
  • R1 an input resistor
  • R2 a RC element consisting of a potentiometer R2 and a capacitor C is connected in the feedback branch.
  • the potentiometer R2 allows the gain and thus the volume setting change on the hearing aid. Simultaneously with the reinforcement however, the cutoff frequency (the knee point) also changes, from which the gain decreases with increasing frequency.
  • Figure 2 shows the gain V over the frequency f for different Potentiometer settings of the amplifier circuit according to FIG. 1.
  • Characteristic curve 1 shows the gain V above frequency f at maximum volume setting. With this setting is the resistance of the potentiometer R2 largest. Up to a cutoff frequency the gain is constant, above the cutoff frequency the gain decreases linearly with increasing frequency.
  • the characteristics 2 and 3 show the gain versus frequency for the normal position (characteristic curve 2) or the minimum position (Characteristic curve 3) of the volume control. As from Figure 2 continues one can see that with decreasing amplification Increase in the cutoff frequency, from which a gain reduction of the higher frequencies.
  • the setting of the gain for hearing aids in the above described way is that in particular with high amplification and high frequencies, more undesirable Whistling feedback occurs.
  • the gain reduction the high frequencies counteract this.
  • the higher the gain the greater the probability for feedback whistles and therefore the beginning the lowering at lower frequencies.
  • the gain reduction method described above is relatively rigid and offers little scope for individual or device-specific adjustment.
  • the effective amplification often depends on other factors in addition to adjusting the volume control.
  • AGC automatic gain control
  • an algorithm for noise suppression can also be provided in a hearing aid, for example, which reduces the gain over a broad band when a noise is detected. This process is exemplified in Figure 2.
  • the gain reduction by a certain amount causes a parallel shift of the preset characteristic curve of the normal gain 2 by exactly this amount. This is illustrated in FIG. 2 by the characteristic curve 4 and the arrow 5. Based on the setting of the volume control in the normal position (characteristic curve 2), the gain is automatically reduced by the signal processing unit, so that the effective system gain illustrated by characteristic curve 4 results. As can also be seen from FIG. 2, the already reduced amplification above the frequency F1 is reduced again.
  • the gain versus frequency is at one Hearing aid according to the invention illustrated.
  • hearing aid in question has a volume control, this is Characteristic preferably a middle position of the volume control assigned so that the hearing aid wearer the Reinforcement based on normal reinforcement by actuation the volume control both to higher gains as well as lower reinforcements.
  • the maximum gain 7 can be stored. This too can the adjustment of the hearing aid by the acoustician and transferred to the hearing aid during programming become.
  • a change in the gain results in a effective gain as exemplified in Figure 3 by the characteristic curve 8 is illustrated.
  • the normal amplification 6 is initially a parallel one Reduction of the gain characteristic by a certain one Amount, e.g. -10 dB, and the lowered characteristic will then from a frequency F2 on the characteristic of the maximum Gain 7 limited. This means that even at high frequencies only a one-time lowering, in contrast to Figure 2, the same situation in a conventional Hearing aid illustrated and in the case of the characteristic curve 4 a two-fold gain reduction above frequency F1 took place.
  • FIG. 4 and 5 show an example in the block diagram Hearing aids with a gain control according to the invention.
  • a microphone 11 which picks up an acoustic signal and in converts an electrical signal.
  • the resulting audio signal is initially a preamplifier and A / D converter unit 12 supplied, in which the initially analog audio signal in a digital audio signal is converted.
  • the digital Audio signal by means of the filter bank 13 in several frequency bands (Channels) divided.
  • the audio signals of the individual Channels are initially signal processing units 14A-14E in which the audio signals e.g. to adapt to the individual hearing loss of a hearing aid wearer varies be filtered.
  • the signal processing units 14A-14E also perform signal analysis to for example to determine the signal level, the current one Detect hearing situation or the presence of noise to recognize.
  • This signal analysis becomes parameters derived and fed roll-off logic units 15A-15E.
  • the latter are also stored in a memory 16 Parameters that include a normal gain as well as a maximum amplification of the audio signal over frequency for identify the respective channel.
  • the normal gain sets the gain calculation for each frequency of the transmittable frequency range a gain output value fixed and can both from a default gain setting by the hearing aid manufacturer as well as in the adjustment of the hearing aid by the acoustician.
  • the maximum gain by the hearing aid manufacturer preset and individually by the acoustician be adjusted.
  • the roll-off logic units 15A-15E also continues the current setting of a Volume control 17 to be supplied. From the roll-off logic units Determine the parameters supplied to 15A-15E a certain gain for each frequency.
  • the invention is in a variety of different ways feasible in terms of circuitry.
  • Another embodiment Figure 5 shows this for this example is in a hearing aid 30 via a microphone 31 acoustic input signal recorded and into an electrical Audio signal converted, that of a preamp and A / D converter unit 32 is supplied.
  • Processing is also carried out here of the audio signal in several parallel channels, which means a filter bank 33 are divided.
  • Signal processing units 34A-34E determined parameters a common roll-off logic unit 35 supplied. These are also stored in a memory 36 Parameters that include the normal gain as well as the maximum Characterize reinforcement. The current also flows Setting the volume control 37 on.
  • Roll-off logic unit 35 calculates incoming parameters these parameters for controlling a variable filter 41, see that also in this embodiment, initially all reinforcement requirements through the reinforcement members 38A-38E are met, however, in contrast to the aforementioned embodiment after merging the audio signals of the individual channels is limited to the maximum gain is realized by means of the variable filter 41, which in turn is controlled by the roll-off logic unit 35 becomes.
  • This exemplary embodiment also takes place, if appropriate a signal post-processing in a signal post-processing unit and the output of the processed audio signal via a handset 40.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Tone Control, Compression And Expansion, Limiting Amplitude (AREA)
  • Control Of Amplification And Gain Control (AREA)
  • Circuits Of Receivers In General (AREA)
  • Mobile Radio Communication Systems (AREA)
EP02013818A 2001-07-02 2002-06-21 Procédé d'utilisation d'une prothèse auditive et une prothèse auditive numérique programmable correspondante Revoked EP1274278B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10131964 2001-07-02
DE10131964A DE10131964B4 (de) 2001-07-02 2001-07-02 Verfahren zum Betrieb eines digitalen programmierbaren Hörgerätes sowie digitales programmierbares Hörgerät

Publications (3)

Publication Number Publication Date
EP1274278A2 true EP1274278A2 (fr) 2003-01-08
EP1274278A3 EP1274278A3 (fr) 2008-07-30
EP1274278B1 EP1274278B1 (fr) 2011-04-27

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EP02013818A Revoked EP1274278B1 (fr) 2001-07-02 2002-06-21 Procédé d'utilisation d'une prothèse auditive et une prothèse auditive numérique programmable correspondante

Country Status (5)

Country Link
US (1) US7068802B2 (fr)
EP (1) EP1274278B1 (fr)
AT (1) ATE507684T1 (fr)
DE (2) DE10131964B4 (fr)
DK (1) DK1274278T3 (fr)

Cited By (2)

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EP2169984A3 (fr) * 2008-09-26 2012-05-30 Siemens Medical Instruments Pte. Ltd. Prothèse auditive avec système de microphone directif et procédé de fonctionnement d'une telle prothèse auditive
EP2717597B1 (fr) 2012-10-08 2020-06-24 Oticon A/s Dispositif d'aide auditive avec un traitement audio dépendant des ondes cérébrales

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JP4402977B2 (ja) * 2003-02-14 2010-01-20 ジーエヌ リザウンド エー／エス 補聴器における動的圧縮
US7809150B2 (en) * 2003-05-27 2010-10-05 Starkey Laboratories, Inc. Method and apparatus to reduce entrainment-related artifacts for hearing assistance systems
AU2004201374B2 (en) * 2004-04-01 2010-12-23 Phonak Ag Audio amplification apparatus
US7756276B2 (en) * 2003-08-20 2010-07-13 Phonak Ag Audio amplification apparatus
DE102004053776B4 (de) 2004-11-08 2007-10-31 Siemens Audiologische Technik Gmbh Verfahren zur Verstärkung eines Akustiksignals und entsprechendes Akustiksystem
DE102005020317B4 (de) * 2005-05-02 2009-04-02 Siemens Audiologische Technik Gmbh Automatische Verstärkungseinstellung bei einem Hörhilfegerät
DE102006007779B4 (de) * 2006-02-20 2008-07-10 Infineon Technologies Ag Filterbank-Anordnung und Signalverarbeitungs-Vorrichtung
US8553899B2 (en) * 2006-03-13 2013-10-08 Starkey Laboratories, Inc. Output phase modulation entrainment containment for digital filters
US8116473B2 (en) 2006-03-13 2012-02-14 Starkey Laboratories, Inc. Output phase modulation entrainment containment for digital filters
US20100056926A1 (en) * 2008-08-26 2010-03-04 Gynesonics, Inc. Ablation device with articulated imaging transducer
DE102006019694B3 (de) 2006-04-27 2007-10-18 Siemens Audiologische Technik Gmbh Verfahren zum Einstellen eines Hörgeräts mit Hochfrequenzverstärkung
DE102006046699B3 (de) * 2006-10-02 2008-01-03 Siemens Audiologische Technik Gmbh Hörvorrichtung mit unsymmetrischer Klangwaage und entsprechendes Einstellverfahren
DE102007003248A1 (de) * 2007-01-23 2008-07-24 GEERS Hörakustik AG & Co. KG Hörgerät
US20090076636A1 (en) * 2007-09-13 2009-03-19 Bionica Corporation Method of enhancing sound for hearing impaired individuals
US20090076804A1 (en) * 2007-09-13 2009-03-19 Bionica Corporation Assistive listening system with memory buffer for instant replay and speech to text conversion
US20090076816A1 (en) * 2007-09-13 2009-03-19 Bionica Corporation Assistive listening system with display and selective visual indicators for sound sources
US20090076825A1 (en) * 2007-09-13 2009-03-19 Bionica Corporation Method of enhancing sound for hearing impaired individuals
US20090074203A1 (en) * 2007-09-13 2009-03-19 Bionica Corporation Method of enhancing sound for hearing impaired individuals
US20090074206A1 (en) * 2007-09-13 2009-03-19 Bionica Corporation Method of enhancing sound for hearing impaired individuals
US20090074214A1 (en) * 2007-09-13 2009-03-19 Bionica Corporation Assistive listening system with plug in enhancement platform and communication port to download user preferred processing algorithms
US20090074216A1 (en) * 2007-09-13 2009-03-19 Bionica Corporation Assistive listening system with programmable hearing aid and wireless handheld programmable digital signal processing device
US9729976B2 (en) * 2009-12-22 2017-08-08 Starkey Laboratories, Inc. Acoustic feedback event monitoring system for hearing assistance devices
US8942398B2 (en) 2010-04-13 2015-01-27 Starkey Laboratories, Inc. Methods and apparatus for early audio feedback cancellation for hearing assistance devices
US9654885B2 (en) 2010-04-13 2017-05-16 Starkey Laboratories, Inc. Methods and apparatus for allocating feedback cancellation resources for hearing assistance devices
US8917891B2 (en) * 2010-04-13 2014-12-23 Starkey Laboratories, Inc. Methods and apparatus for allocating feedback cancellation resources for hearing assistance devices
US8675900B2 (en) * 2010-06-04 2014-03-18 Exsilent Research B.V. Hearing system and method as well as ear-level device and control device applied therein
CN106851512B (zh) * 2010-10-14 2020-11-10 索诺瓦公司 调整听力设备的方法及根据所述方法可操作的听力设备
KR20150117114A (ko) * 2014-04-09 2015-10-19 한국전자통신연구원 잡음 제거 장치 및 방법
US10382872B2 (en) 2017-08-31 2019-08-13 Starkey Laboratories, Inc. Hearing device with user driven settings adjustment
DE102021208643B4 (de) 2021-08-09 2023-02-16 Sivantos Pte. Ltd. Verfahren zur Anpassung eines digitalen Hörgerätes, Hörgerät und Computerprogrammprodukt

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Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2169984A3 (fr) * 2008-09-26 2012-05-30 Siemens Medical Instruments Pte. Ltd. Prothèse auditive avec système de microphone directif et procédé de fonctionnement d'une telle prothèse auditive
EP2717597B1 (fr) 2012-10-08 2020-06-24 Oticon A/s Dispositif d'aide auditive avec un traitement audio dépendant des ondes cérébrales
EP2717597B2 (fr) † 2012-10-08 2023-08-09 Oticon A/s Dispositif d'aide auditive avec un traitement audio dépendant des ondes cérébrales

Also Published As

Publication number Publication date
DK1274278T3 (da) 2011-08-15
ATE507684T1 (de) 2011-05-15
EP1274278A3 (fr) 2008-07-30
US20030002699A1 (en) 2003-01-02
DE10131964A1 (de) 2003-01-30
DE50215025D1 (de) 2011-06-09
DE10131964B4 (de) 2005-11-03
EP1274278B1 (fr) 2011-04-27
US7068802B2 (en) 2006-06-27

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