EP1558059A2 - Contrôle de gain dans une prothèse auditive - Google Patents
Contrôle de gain dans une prothèse auditive Download PDFInfo
- Publication number
- EP1558059A2 EP1558059A2 EP05405298A EP05405298A EP1558059A2 EP 1558059 A2 EP1558059 A2 EP 1558059A2 EP 05405298 A EP05405298 A EP 05405298A EP 05405298 A EP05405298 A EP 05405298A EP 1558059 A2 EP1558059 A2 EP 1558059A2
- Authority
- EP
- European Patent Office
- Prior art keywords
- hearing instrument
- gain
- active
- signal
- user
- 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
Links
- 238000000034 method Methods 0.000 claims description 16
- 230000001419 dependent effect Effects 0.000 claims description 8
- 230000005236 sound signal Effects 0.000 claims 2
- 230000003321 amplification Effects 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- 238000003199 nucleic acid amplification method Methods 0.000 description 3
- 238000010586 diagram Methods 0.000 description 2
- 230000000977 initiatory effect Effects 0.000 description 2
- 230000008054 signal transmission Effects 0.000 description 2
- 238000001228 spectrum Methods 0.000 description 2
- 208000000477 Bilateral Hearing Loss Diseases 0.000 description 1
- 208000032953 Device battery issue Diseases 0.000 description 1
- 230000006978 adaptation Effects 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 210000005069 ears Anatomy 0.000 description 1
- 239000011521 glass Substances 0.000 description 1
- 230000001939 inductive effect Effects 0.000 description 1
- 230000008447 perception Effects 0.000 description 1
- 230000001629 suppression Effects 0.000 description 1
- 230000001225 therapeutic effect Effects 0.000 description 1
- 230000036962 time dependent Effects 0.000 description 1
Images
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
- H04R25/552—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
- H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
-
- 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
- H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
- H04R2460/03—Aspects of the reduction of energy consumption in hearing devices
Definitions
- This invention is in the field of processing signals in or for hearing instruments. It more particularly relates to a method of controlling a gain setting in a hearing instrument, and to a hearing instrument.
- Binaural loudness summation is known in the field of audiology. Binaural loudness summation is the effect that the loudness of sound is greater when it is presented to both ears simultaneously than when it is presented to one ear alone. The magnitude of this effect varies between individuals. Usually, the increase in loudness is approximately 3 dB when the intensity level is near the person's hearing threshold. The effect increases at suprathreshold level.
- Binaural loudness summation is one of the advantages of binaural amplification. For persons with bilateral hearing loss who are equipped with two hearing instruments, the applied gain may be reduced. Due to the reduced gain, the chance of feedback is decreased, and larger vents may be used.
- the loss of binaural loudness summation accounts for a non-ideal gain fitting if a user, who usually wears two hearing instruments, occasionally only uses one hearing instrument. This may happen if the user deliberately only wears one hearing instrument or if one of the hearing instruments is not available.
- a hearing instrument in a hearing instrument it is once or repeatedly checked whether a second hearing instrument is present and active. If a second hearing instrument is active on the contralateral side, a first gain setting is adopted. If, however, no further hearing instrument is found to be active, a second gain setting is chosen.
- the gain generated by the hearing instrument with the first gain setting may correspond to the gain for binaural fitting, whereas the gain of the second gain setting is increased in comparison.
- the second gain may simply correspond to the first gain increased by a certain dB value. It may as an alternative be a specifically adapted gain characteristic of a monaural fitting for the user.
- Gain is usually defined as the ratio between an input signal and an output signal. This ratio may be time-dependent and/or may be frequency dependent. In addition, the gain may be situation dependent (i.e. different gain settings for different hearing programs, which are associated to different acoustic situations).
- a wireless communication channel may be a radio signal transmission or an inductive signal transmission (i.e., using magnetically coupled coils as antennas) or any other suitable wireless communication channel.
- the signal used may be any signal transmitting any information.
- the signal may just be a characteristic regularly repeated presence signal (e.g. a radio frequency carrier signal).
- a wired communication channel may for example comprise a physical wire or may comprise the frame of a user's glasses.
- the communication channel Since the only information that has to be transmitted is whether or not a second hearing instrument is active, the communication channel does not have to have a large bandwidth. Compared to prior art communication channels between two hearing instruments, the communication channel may therefore consume comparatively little power.
- the remaining hearing instrument may, according to a special embodiment of the invention, initiate a signal informing the user of the battery failure of the unavailable hearing instrument and reminding the user to replace the battery of said hearing instrument.
- a signal may be a beep signal, a voice message (like for example "left hearing aid not available” or "change battery of left hearing aid” etc.), a message displayed on a display unit of a remote control etc.
- the battery charge level in a hearing aid is a quantity that is difficult to measure, at least without extra hardware, so that the "battery-low" warning signals are often unreliable.
- a warning signal of this kind is, of course, not produced upon every check but for example only once when the other hearing instrument is found to be unavailable for the first time.
- the occurrence of such a signal may but does not have to depend on a manually set switch value. For example, the user may switch to a monaural mode in which he deliberately uses one hearing instrument only, in which case a signal will not be output.
- a signal warning the user of failure or imminent failure of the other hearing instrument may also be initiated in situations where, in contrast to the above-described principle, the gain setting of the remaining hearing instrument is not adapted in case the other hearing instrument is inactive.
- hearing instrument or “hearing device”, as understood here, denotes on the one hand hearing aid devices that are therapeutic devices improving the hearing ability of individuals, primarily according to diagnostic results.
- Such hearing aid devices may be Behind-The-Ear hearing aid devices or In-The-Ear hearing aid devices (including the so called In-The-Canal and Completely-In-The-Canal hearing aid devices, as well as partially and fully implanted hearing aid devices).
- the term stands for devices which may improve the hearing of individuals with normal hearing e.g. in specific acoustical situations as in a very noisy environment or in concert halls, or which may even be used in the context of remote communication or of audio listening, for instance as provided by headphones.
- the hearing devices addressed by the present invention are so-called active hearing devices which comprise at the input side at least one acoustical to electrical converter, such as a microphone, at the output side at least one electrical to acoustical converter, such as a loudspeaker (often also termed “receiver"), and which further comprise a signal processing unit for processing signals according to the output signals of the acoustical to electrical converter and for generating output signals to the electrical input of the electrical to mechanical output converter.
- the signal processing circuit may be an analog, digital or hybrid analog-digital circuit, and may be implemented with discrete electronic components, integrated circuits, or a combination of both.
- the hearing instrument system of Figure 1 comprises a set of two hearing instruments, each including at least one acoustic-to-electric converter 1.1, 1.2 (often, two or even three acoustic-to-electric converters are available in each hearing instrument), a signal processing unit (SPU) 3.1, 3.2 operable to apply a time- and/or frequency-dependent gain to the input signal or input signals S I,1 , S I,2 resulting in output signal S O,1 , S O,2 and at least one electric-to-acoustic converter 5.1, 5.2.
- a communication channel 6 by which the hearing instruments may exchange information.
- the communication interfaces of the hearing instruments are denoted by 7.1 and 7.2.
- FIG. 2 An embodiment of the method according to the invention - as implemented in at least one, preferably in both of the hearing instruments - is illustrated in Figure 2 .
- a check 12 is carried out by the hearing instrument via the communication channel.
- the check it is determined whether the second hearing instrument is active. For example, it is checked whether a characteristic signal is received by a coil serving as antenna.
- the overall gain setting - which may in addition depend on other parameters such as stored, pre-set user specific values, detected noise, incoming sound direction, a loudness level or an amplification level pre-set by the user etc.
- a first gain setting 13 is applied in the case both hearing instruments are functional.
- the first gain setting is adapted to binaural hearing and accounts for the phenomenon of binaural loudness summation.
- a second gain setting 14 is applied.
- the second gain setting may be qualitatively different from the first gain setting and may be based on different parameters (for example on different noise suppression algorithms, on different time constants, etc.). It may as an alternative be calculated from the first gain setting in an appropriate way, for example by adding a loudness and frequency dependent value to the gain.
- the second gain (corresponding to the second gain setting) is higher compared to the first gain.
- the gain is frequency dependent, this means that an average of the gain the audible part of the sound spectrum is higher.
- the second gain may be specifically adapted to monaural hearing and to the characteristic hearing ability of the ear to which the remaining hearing instrument is associated.
- the second gain and possibly also the first gain need not be identical for both hearing instruments of a hearing instrument system.
- An example of a gain increase in case of a frequency dependent gain is illustrated very schematically in Figure 3 .
- a first gain curve 23 depicts the frequency dependence of the first gain
- a second gain curve 24 shows the frequency dependence of the second gain.
- the second gain does not have to be higher than the first gain for all frequencies, although preferably in the part of the frequency spectrum which is most important for speech perception for the user, the second gain is on average higher than the first gain.
- the step of checking whether both hearing instruments are functional is preferably repeated regularly.
- a status information of a hearing instrument is transmitted to the other hearing instrument proactively, at regular intervals or on special occasions, such as in case of imminent failure (for example before the battery is empty).
- a status information tag (or the like) in a memory of the receiving hearing instrument may be set to "not active” (referring to the other hearing instrument).
- the step of determining whether the other hearing instrument is active then includes internally checking the status information tag.
- the status information tag is re-set to "active" - for example manually or by a status information transmission by the other hearing instrument when it is switched on - when the other hearing instrument is activated again.
- the hearing instrument may optionally once or repeatedly produce a signal 15 when the check reveals that the other hearing instrument is not active.
- the signal may for example be acoustical or may be a warning message displayed on a display field of a remote control (not shown). By the signal, the user may for example be reminded by the still functioning hearing aid to replace the battery of the other hearing instrument.
- the hearing instrument may manually be set to a mode where the signal does not appear so that the user is not disturbed by the signal in situations where he deliberately only uses only one hearing instrument.
- FIG. 4 A second embodiment of the method according to the invention is shown in Figure 4 .
- the embodiment of Figure 4 may be viewed as special, particularly simple variant of the embodiment of Figure 2.
- a check 12 is carried out by the hearing instrument via the communication channel.
- a gain setting determination 31 - the gain may again depend on parameters such as be fixedly stored, for example user-characteristic values, detected noise, incoming sound direction a loudness level or amplification level pre-set by the user etc. - is carried out before or after or simultaneously to the check. If the check reveals that the other hearing instrument is not active, the gain is increased 32 in a predetermined manner. It may for example be increased by adding a fixed dB value (for example between 2 dB and 5 dB) for all frequencies. This is illustrated in Figure 5 , where the second gain curve 44 corresponds to the first gain curve plus a fixed value which is constant for all frequencies. As an alternative, a fixed value which depends on the frequency may be added.
- the embodiment of Figure 4 features the advantage that it is relatively simple. Also the embodiment of Figure 4 may comprise providing a signal 15 when it has been found that the other hearing instrument is not active.
- a process of the kind shown in Figures 2 and 4 may be carried out in both hearing instruments. If one hearing instrument fails, the other one will switch to the second gain (or the increased gain).
- a hearing instrument according to the invention comprises means for carrying out any embodiment of the above described method.
- a hearing instrument system comprises two hearing instruments, shaped and adapted to be placed behind or in the left and right ear of the user, respectively.
- the communication interfaces of the two hearing instruments are for example adjusted to each other so that only signals of the corresponding hearing instruments of the hearing instrument system may be detected or that signals of hearing instruments of other hearing instrument systems - for example of hearing instruments worn by other persons nearby - may be distinguished.
- universal interfaces may be used, so that upon replacement of one hearing instrument no adaptation has to be done.
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- Health & Medical Sciences (AREA)
- General Health & Medical Sciences (AREA)
- Otolaryngology (AREA)
- Engineering & Computer Science (AREA)
- Neurosurgery (AREA)
- Physics & Mathematics (AREA)
- Acoustics & Sound (AREA)
- Signal Processing (AREA)
- Computer Networks & Wireless Communication (AREA)
- Stereophonic System (AREA)
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DK05405298T DK1558059T3 (da) | 2005-04-18 | 2005-04-18 | Styring af en forstærkningsindstilling i et høreapparat |
EP20050405298 EP1558059B1 (fr) | 2005-04-18 | 2005-04-18 | Contrôle de gain dans une prothèse auditive |
DE200560021835 DE602005021835D1 (de) | 2005-04-18 | 2005-04-18 | Verstärkungseinstellungskontrolle für einen Hörinstrument |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP20050405298 EP1558059B1 (fr) | 2005-04-18 | 2005-04-18 | Contrôle de gain dans une prothèse auditive |
Publications (3)
Publication Number | Publication Date |
---|---|
EP1558059A2 true EP1558059A2 (fr) | 2005-07-27 |
EP1558059A3 EP1558059A3 (fr) | 2005-11-23 |
EP1558059B1 EP1558059B1 (fr) | 2010-06-16 |
Family
ID=34626583
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP20050405298 Not-in-force EP1558059B1 (fr) | 2005-04-18 | 2005-04-18 | Contrôle de gain dans une prothèse auditive |
Country Status (3)
Country | Link |
---|---|
EP (1) | EP1558059B1 (fr) |
DE (1) | DE602005021835D1 (fr) |
DK (1) | DK1558059T3 (fr) |
Cited By (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2008006772A2 (fr) * | 2006-07-12 | 2008-01-17 | Phonak Ag | Procédé de fonctionnement d'un système auditif binauriculaire ainsi qu'un système d'écoute binauriculaire |
WO2008071231A1 (fr) * | 2006-12-13 | 2008-06-19 | Phonak Ag | Procédé et système pour le réglage d'un dispositif auditif |
EP2147568A1 (fr) * | 2007-05-07 | 2010-01-27 | 3M Svenska Aktiebolag | Procédé et appareil d'amortissement d'un signal sonore |
EP2293599A1 (fr) * | 2009-05-25 | 2011-03-09 | Panasonic Corporation | Système de prothèse auditive |
US8223994B2 (en) | 2006-07-12 | 2012-07-17 | 3M Svenska Aktiebolag | Method of limiting the maximum permitted sound volume in an earphone, and an earphone for carrying out the method |
CN102970636A (zh) * | 2011-08-31 | 2013-03-13 | 索尼公司 | 声音再现装置 |
US9451350B2 (en) | 2011-08-31 | 2016-09-20 | Sony Corporation | Earphone device |
US11089411B2 (en) | 2018-12-14 | 2021-08-10 | Sonova Ag | Systems and methods for coordinating rendering of a remote audio stream by binaural hearing devices |
US11510020B2 (en) | 2018-12-14 | 2022-11-22 | Sonova Ag | Systems and methods for coordinating rendering of a remote audio stream by binaural hearing devices |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0941014A2 (fr) * | 1998-03-03 | 1999-09-08 | Siemens Audiologische Technik GmbH | Système d'appareil auditif avec deux prothèses auditives et méthode de fonctionnement d'un tel système auditif |
EP1465454A2 (fr) * | 2003-04-01 | 2004-10-06 | Gennum Corporation | Système et procédé pour détecter l'insertion ou le retrait d'une prothèse auditive du conduit auditif |
WO2004110099A2 (fr) * | 2003-06-06 | 2004-12-16 | Gn Resound A/S | Reseau sans fil pour une prothese auditive |
WO2004114722A1 (fr) * | 2003-06-24 | 2004-12-29 | Gn Resound A/S | Systeme de prothese auditive binaural a traitement sonore coordonne |
-
2005
- 2005-04-18 EP EP20050405298 patent/EP1558059B1/fr not_active Not-in-force
- 2005-04-18 DK DK05405298T patent/DK1558059T3/da active
- 2005-04-18 DE DE200560021835 patent/DE602005021835D1/de active Active
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0941014A2 (fr) * | 1998-03-03 | 1999-09-08 | Siemens Audiologische Technik GmbH | Système d'appareil auditif avec deux prothèses auditives et méthode de fonctionnement d'un tel système auditif |
EP1465454A2 (fr) * | 2003-04-01 | 2004-10-06 | Gennum Corporation | Système et procédé pour détecter l'insertion ou le retrait d'une prothèse auditive du conduit auditif |
WO2004110099A2 (fr) * | 2003-06-06 | 2004-12-16 | Gn Resound A/S | Reseau sans fil pour une prothese auditive |
WO2004114722A1 (fr) * | 2003-06-24 | 2004-12-29 | Gn Resound A/S | Systeme de prothese auditive binaural a traitement sonore coordonne |
Non-Patent Citations (1)
Title |
---|
THOMAS A. POWERS, PAMELA BURTON: "Wireless technology designed to provide true binaural amplification" THE HEARING JOURNAL, [Online] vol. 58, 1 January 2005 (2005-01-01), XP002345661 Retrieved from the Internet: URL:http://www.siemens-hearing.com/_common /pdf/WP_HJ0105.pdf> [retrieved on 2005-09-19] * |
Cited By (20)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP2039218B1 (fr) | 2006-07-12 | 2020-12-02 | Sonova AG | Procede de fonctionnement d'un systeme d'ecoute binauriculaire ainsi qu'un systeme d'ecoute binauriculaire |
WO2008006772A3 (fr) * | 2006-07-12 | 2008-02-28 | Phonak Ag | Procédé de fonctionnement d'un système auditif binauriculaire ainsi qu'un système d'écoute binauriculaire |
US8223994B2 (en) | 2006-07-12 | 2012-07-17 | 3M Svenska Aktiebolag | Method of limiting the maximum permitted sound volume in an earphone, and an earphone for carrying out the method |
US8295497B2 (en) | 2006-07-12 | 2012-10-23 | Phonak Ag | Method for operating a binaural hearing system as well as a binaural hearing system |
WO2008006772A2 (fr) * | 2006-07-12 | 2008-01-17 | Phonak Ag | Procédé de fonctionnement d'un système auditif binauriculaire ainsi qu'un système d'écoute binauriculaire |
WO2008071231A1 (fr) * | 2006-12-13 | 2008-06-19 | Phonak Ag | Procédé et système pour le réglage d'un dispositif auditif |
EP2147568A1 (fr) * | 2007-05-07 | 2010-01-27 | 3M Svenska Aktiebolag | Procédé et appareil d'amortissement d'un signal sonore |
EP2147568A4 (fr) * | 2007-05-07 | 2012-01-25 | 3M Svenska Ab | Procédé et appareil d'amortissement d'un signal sonore |
EP2293599A1 (fr) * | 2009-05-25 | 2011-03-09 | Panasonic Corporation | Système de prothèse auditive |
EP2293599A4 (fr) * | 2009-05-25 | 2011-06-22 | Panasonic Corp | Système de prothèse auditive |
US8050439B2 (en) | 2009-05-25 | 2011-11-01 | Panasonic Corporation | Hearing aid system |
CN102970636A (zh) * | 2011-08-31 | 2013-03-13 | 索尼公司 | 声音再现装置 |
EP2566185A3 (fr) * | 2011-08-31 | 2013-12-25 | Sony Corporation | Dispositif de reproduction sonore |
US8976987B2 (en) | 2011-08-31 | 2015-03-10 | Sony Corporation | Sound reproduction device |
US9451350B2 (en) | 2011-08-31 | 2016-09-20 | Sony Corporation | Earphone device |
US9578410B2 (en) | 2011-08-31 | 2017-02-21 | Sony Corporation | Sound reproduction device |
US10212504B2 (en) | 2011-08-31 | 2019-02-19 | Sony Corporation | Earphone device |
JP2013051624A (ja) * | 2011-08-31 | 2013-03-14 | Sony Corp | 音響再生装置 |
US11089411B2 (en) | 2018-12-14 | 2021-08-10 | Sonova Ag | Systems and methods for coordinating rendering of a remote audio stream by binaural hearing devices |
US11510020B2 (en) | 2018-12-14 | 2022-11-22 | Sonova Ag | Systems and methods for coordinating rendering of a remote audio stream by binaural hearing devices |
Also Published As
Publication number | Publication date |
---|---|
EP1558059B1 (fr) | 2010-06-16 |
EP1558059A3 (fr) | 2005-11-23 |
DK1558059T3 (da) | 2010-10-11 |
DE602005021835D1 (de) | 2010-07-29 |
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