EP2822300A1 - Reconnaissance de situations d'écoute à l'aide de différentes sources de signal - Google Patents

Reconnaissance de situations d'écoute à l'aide de différentes sources de signal Download PDF

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Publication number
EP2822300A1
EP2822300A1 EP20140172917 EP14172917A EP2822300A1 EP 2822300 A1 EP2822300 A1 EP 2822300A1 EP 20140172917 EP20140172917 EP 20140172917 EP 14172917 A EP14172917 A EP 14172917A EP 2822300 A1 EP2822300 A1 EP 2822300A1
Authority
EP
European Patent Office
Prior art keywords
signal
electrical
electrical signal
correlation
hearing aid
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
EP20140172917
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German (de)
English (en)
Other versions
EP2822300B1 (fr
Inventor
Roland Barthel
Matthias Müller-Wehlau
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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Publication date
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Publication of EP2822300A1 publication Critical patent/EP2822300A1/fr
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Publication of EP2822300B1 publication Critical patent/EP2822300B1/fr
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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
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • 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
    • H04R25/43—Electronic input selection or mixing based on input signal analysis, e.g. mixing or selection between microphone and telecoil or between microphones with different directivity characteristics
    • 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
    • H04R25/45—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; 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
    • H04R25/55—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 invention relates to a hearing aid, wherein the hearing aid has an acousto-electrical converter for converting a sound signal into a first electrical signal and a recording device for receiving an electrical or electromagnetic signal and conversion into a second electrical signal. Furthermore, the hearing aid device has a classification device, wherein the signal estimation device is in signal connection with the acousto-electrical converter and the recording device. The hearing aid device also has a signal processing device, wherein the signal processing device is in signal connection with the acoustoelectric transducer, the recording device and the signal estimation device and is designed to receive the first and the second electrical signal and to process it into a third electrical signal. Finally, the hearing aid has an electro-mechanical transducer, which is in signal communication with the signal processing device and is designed to convert the third electrical signal into a sound signal and output.
  • 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 (Hd0), hearing aid with external handset (RIC: receiver in the canal) and in-the-ear hearing aids (Id0), for example Concha hearing aids or canal hearing aids (ITE, CIC).
  • Hd0 behind-the-ear hearing aids
  • RIC hearing aid with external handset
  • Id0 in-the-ear hearing aids
  • ITE Concha hearing aids or 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 an acousto-electrical converter, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually as an electro-acoustic transducer, z. B. miniature speaker, or as an electro-mechanical transducer, z. B. bone conduction, realized.
  • the amplifier is usually integrated in a signal processing device.
  • simultaneous arrival of sound wave and electromagnetic signal may interfere with the hearing, if both signals originate from a common source, such as a TV with speakers and simultaneous infrared or Bluetooth transmission, and thereby the direct acoustic and the hearing aid decoded electromagnetic signal get to the eardrum with different time delay. It does not matter whether the acoustic signal comes directly to the eardrum, for example, by a ventilation hole in an earmold, by an open supply or after processing via microphone, signal processing and electromechanical converter. The time delay then leads, for example by interference to extinction or amplification of signals as a function of frequency.
  • a hearing device with a microphone and a receiving device for receiving an electrical or electromagnetic signal has a signal estimation device, which recognizes the signals of the microphone and the receiving device and by evaluating the signals based on the level and / or correlation of a hearing situation and activates a corresponding hearing program such as noise relief or feedback suppression. For example, it is proposed to evaluate the hearing situation solely on the basis of the microphone signal given a high correlation of the signals.
  • the known hearing programs are not designed to detect and reduce problems that arise only after the signal processing in the hearing device in the ear itself as a function of the hearing situation.
  • a hearing aid that has a microphone and an external signal input.
  • the hearing aid further includes a mixer for mixing the two input signals. and a comparison unit to determine if the signal from the microphone is that of the external signal input.
  • a mixing decision unit connected to the comparing unit decides a mixing ratio of microphone signal and signal of the external signal input
  • the object of the present invention is therefore to provide a hearing device that offers the wearer a better hearing in a listening situation with simultaneous acoustic and electrical or electromagnetic transmission of an input signal.
  • this object is achieved by a hearing aid according to claim 1 and a method for operating the hearing aid according to claim 8.
  • the hearing aid according to the invention has an acousto-electrical converter for converting a sound signal into a first electrical signal and a recording device for receiving an electrical or electromagnetic signal and conversion into a second electrical signal. Furthermore, the hearing aid has a signal estimation device, wherein the signal estimation device is in signal connection with the acousto-electrical converter and the recording device. In addition, the hearing aid has a signal processing device which is in signal connection with the acousto-electrical converter, the recording device and the signal estimation device and is designed to receive the first and the second electrical signal and to process a third electrical signal. The hearing aid device finally has an electro-mechanical transducer, which is in signal connection with the signal processing device and is designed to convert the third electrical signal into a sound signal and output.
  • the signal estimation device is designed to determine a correlation of the first and the second electrical signal and to transmit the correlation of the signal processing device, wherein the signal processing device is designed, a portion of the first and the second electrical signal to the third electrical signal as a function of the correlation adjust.
  • the hearing aid according to the invention can make the composition of the third signal and thus of the output signal on the listener dependent on whether the electrical / electromagnetic signal transmission and the acoustic signals transmit associated signals and therefore can interfere.
  • the signal processing device is designed to reduce the proportion of the second electrical signal at the third electrical signal with increasing correlation.
  • the phase-shifted and / or delayed electrically transmitted Signal no longer or only to a small extent in interference with the directly on the eardrum or from the Microphone received acoustic signal can occur and thereby less distorted.
  • the hearing aid is designed to determine the correlation in a first predetermined frequency range.
  • the signal processing device is designed to set the proportion of the first and the second electrical signal to the third electrical signal in a predetermined second frequency range. It is conceivable that the first and the second frequency range are different.
  • the second frequency range is predetermined in whole or in part below the first frequency range.
  • Fig. 1 shows the basic structure of a hearing aid 110 according to the invention.
  • a hearing aid housing 1 for carrying behind the ear are one or more microphones 2 for receiving the sound or acoustic signals from the environment installed.
  • the microphones 2 are acousto-electrical converters 2 for converting the sound into first electrical signals.
  • the hearing aid device 110 has a receiving device 6 for receiving an electrical or electromagnetic signal and conversion into a second electrical signal.
  • a signal processing device 3 which is also integrated in the hearing aid housing 1, processes the first electrical signals and is for this purpose in signal communication with the microphone 2 and the recording device 6.
  • the output signal of the signal processing device 3 is transmitted to a loudspeaker 4 emits 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. Also conceivable, in addition to the electro-acoustic and other electro-mechanical transducers, such as bone conduction.
  • the power supply of the hearing device, and in particular that of the signal processing device 3, is effected by a battery 5 likewise integrated in the hearing device housing 1.
  • the hearing aid device 110 also has a signal estimation device 7, which, as in FIG Fig. 1 is shown part of the signal processing device 3, or is also designed as a separate signal estimation device 7 in the hearing aid 110.
  • the further signal processing functions of the signal processing 3 are shown as function block 12.
  • the signal estimation device 7 is in signal connection with the microphone 2 and the recording device 6.
  • the signal estimation device 7 is designed to determine a correlation between the first electrical signal 10 of the microphone 2 and the second electrical signal 11 of the recording device 6. The result of the classification is transmitted by the signal estimating device 7 to the signal processing device 3 via a signal connection.
  • Fig. 2 shows a schematic flowchart of a method according to the invention.
  • step S10 a sound signal is picked up via a microphone 2 and converted into a first electrical signal 10.
  • step S20 an electrical or electromagnetic signal is received with acoustic information via the recording device 6 and converted into a second electrical signal 11.
  • step S40 a correlation of the first electrical signal 10 and the second electrical signal 11 is determined by the signal estimation device 7 with a method for correlation measurement, as described for example in Wikipedia under the keyword "correlation coefficient”.
  • step S50 the signal processing means 3 receives the first electrical signal 10, the second electrical signal 11, and a signal indicative of the correlation determined in step S40.
  • the signal processing device performs the necessary in a hearing aid 110 to compensate for the hearing loss processing steps such as adjustment of the frequency response, gain or noise suppression.
  • a proportion of the first electrical signal 10 and the second electrical signal 11 is set to a third electrical signal as a function of the correlation. Preferred way takes while the proportion of the second electrical signal 11 to the third electrical signal decreases with increasing correlation. But there are also other mixing ratios conceivable.
  • step S70 an output of the third electrical signal via the handset 4, which converts it into sound waves.
  • the Fig. 3 shows a schematic flowchart of another method according to the invention, which is supplemented by the steps S30 and S60, but otherwise the method of Fig. 2 equivalent.
  • step S30 the first electrical signal 10 and the second electrical signal 11 in filter banks 8 are split into signals for individual, separate or partially overlapping frequency ranges.
  • step S40 it is possible to determine the correlation in a first or more of the frequency ranges.
  • step S50 it is possible to set the ratio of the first electrical signal 10 and the second electrical signal 11 to the third electrical signal depending on the determined correlation in a second or more frequency ranges.
  • the second frequency range or the plurality of frequency ranges for the adjustment is below the first frequency range.
  • step S60 the frequency ranges of the third electrical signal processed in step S50 are again synthesized in a filter bank into a single third electrical signal comprising a plurality of frequency ranges.
  • Fig. 4 shows an illustration of a hearing aid according to the invention in function blocks for carrying out the method Fig. 4
  • the hearing aid device 110 has a microphone 2 or an acousto-electrical converter 2 for converting a sound signal into a first electrical signal and a recording device 6 for receiving an electrical or electromagnetic signal and conversion into a second electrical signal.
  • the first electrical signal 10 and the second electrical signal 11 are supplied to a signal processing device 3, which is part of the hearing aid device 110.
  • the first electrical signal 10 and the second electrical signal 11 are divided by filter banks 8 into a plurality of first signals 10 and second signals 11 into a plurality of frequency ranges.
  • the filter banks 8 can be effected for example by a fast Fourier transformation in a signal processor of the signal processing device 3. It is possible that only a lower and an upper frequency band are generated, wherein the frequencies of the lower frequency band are below the frequencies of the upper frequency band. It is also conceivable that both frequency bands do not overlap or only on the edge. But it is also possible that a plurality of signals in divergent or only slightly overlapping frequency bands is generated.
  • the first electrical signals 10 and the second electrical signals 11 are supplied to a signal estimation device 7.
  • the signal estimation device 7 preferably determines in a first frequency band a correlation of the first signals 10 and second signals 11 and outputs a signal to the signal processing device 3, which represents a measure of the particular correlation.
  • the correlation for several of the frequency bands or a whole transmitted frequency range is determined.
  • the determination of the correlation can be done, for example, with a method for correlation measurement, as described in Wikipedia under the keyword "correlation coefficient”.
  • the signal estimation device 7 is in signal connection with a function block 12, which represents the further signal processing functions.
  • the function block 12 receives the first electrical signals 10 and the second electrical signals 11 and a signal of the signal estimation device 7, which represents a measure of the correlation of the first electrical signal 10 and the second electrical signal 11.
  • the function block 12 generates a third electrical signal from these signals, the function block 12 setting a portion of the first and second electrical signals 11, 12 on the third electrical signal as a function of the correlation, wherein the function block 12 with increasing correlation a share of second electrical signal 11 reduced at the third electrical signal.
  • the function block 12 sets the proportion of the first and the second electrical signal 10, 11 to the third electrical signal in a predetermined second frequency range, wherein the second frequency range is predetermined in whole or in part below the first frequency range.
  • the second frequency range is preferably located at the lower end of the audible spectrum, for example below 1000 Hz, 800 Hz, 500 Hz or even 200 Hz.
  • This frequency range is characterized in that its sound waves with the specified frequencies are preferred when the supply is open or through a ventilation bore directly can get to the eardrum and thus can come into interference with the output from the listener sound waves. Therefore, the upper limit frequency of the second frequency range in particular depends on the properties of the hearing aid, for example on the geometry of the ventilation bore.
  • the functional block 12 also performs other signal processing functions commonly required in a hearing aid 110 to improve the hearing of the wearer. This is for example a frequency-dependent Amplification of the third signal to compensate for a reduction in the sensitivity of the hearing of the wearer and to produce a sufficiently high level for outputting the signal as sound via the handset 4.
  • the individual frequency bands are also combined to form a single output signal by means of a synthesis function.
  • noise suppression adaptive filters
  • feedback or echo compensation and others.
  • the hearing aid device 110 can also be part of a binaural hearing aid system, in which case the signal estimation device 7 could, for example, use the first electrical signals of both hearing aid devices 110 and the result of the classification is used in the same way on both hearing aid devices as illustrated.
  • a combination with other binaural functions such as adaptive directional microphones and functions for improving spatial hearing is also conceivable.

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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)
  • Circuit For Audible Band Transducer (AREA)
EP14172917.8A 2013-07-02 2014-06-18 Reconnaissance de situations d'écoute à l'aide de différentes sources de signal Active EP2822300B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102013212853.3A DE102013212853A1 (de) 2013-07-02 2013-07-02 Erkennen von Hörsituationen mit unterschiedlichen Signalquellen

Publications (2)

Publication Number Publication Date
EP2822300A1 true EP2822300A1 (fr) 2015-01-07
EP2822300B1 EP2822300B1 (fr) 2017-04-19

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EP14172917.8A Active EP2822300B1 (fr) 2013-07-02 2014-06-18 Reconnaissance de situations d'écoute à l'aide de différentes sources de signal

Country Status (4)

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US (1) US9565501B2 (fr)
EP (1) EP2822300B1 (fr)
DE (1) DE102013212853A1 (fr)
DK (1) DK2822300T3 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3364668A1 (fr) * 2017-02-16 2018-08-22 Sivantos Pte. Ltd. Procédé de fonctionnement d'un dispositif auditif et dispositif auditif

Families Citing this family (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9571941B2 (en) * 2013-08-19 2017-02-14 Knowles Electronics, Llc Dynamic driver in hearing instrument
US10538988B2 (en) * 2016-05-31 2020-01-21 Schlumberger Technology Corporation Expandable downhole seat assembly
DK3373603T3 (da) * 2017-03-09 2020-09-14 Oticon As Høreanordning, der omfatter en trådløs lydmodtager

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090296965A1 (en) * 2008-05-27 2009-12-03 Mariko Kojima Hearing aid, and hearing-aid processing method and integrated circuit for hearing aid
EP2182741A1 (fr) 2008-10-28 2010-05-05 Siemens Medical Instruments Pte. Ltd. Dispositif auditif doté d'une unité de reconnaissance de situation spéciale et procédé de fonctionnement d'un dispositif auditif
US20110142268A1 (en) * 2009-06-08 2011-06-16 Kaoru Iwakuni Hearing aid, relay device, hearing-aid system, hearing-aid method, program, and integrated circuit
US20120114155A1 (en) 2010-11-04 2012-05-10 Makoto Nishizaki Hearing aid
US20130094683A1 (en) * 2011-10-17 2013-04-18 Oticon A/S Listening system adapted for real-time communication providing spatial information in an audio stream

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090296965A1 (en) * 2008-05-27 2009-12-03 Mariko Kojima Hearing aid, and hearing-aid processing method and integrated circuit for hearing aid
EP2182741A1 (fr) 2008-10-28 2010-05-05 Siemens Medical Instruments Pte. Ltd. Dispositif auditif doté d'une unité de reconnaissance de situation spéciale et procédé de fonctionnement d'un dispositif auditif
US20110142268A1 (en) * 2009-06-08 2011-06-16 Kaoru Iwakuni Hearing aid, relay device, hearing-aid system, hearing-aid method, program, and integrated circuit
US20120114155A1 (en) 2010-11-04 2012-05-10 Makoto Nishizaki Hearing aid
US20130094683A1 (en) * 2011-10-17 2013-04-18 Oticon A/S Listening system adapted for real-time communication providing spatial information in an audio stream

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3364668A1 (fr) * 2017-02-16 2018-08-22 Sivantos Pte. Ltd. Procédé de fonctionnement d'un dispositif auditif et dispositif auditif

Also Published As

Publication number Publication date
EP2822300B1 (fr) 2017-04-19
US20150010182A1 (en) 2015-01-08
US9565501B2 (en) 2017-02-07
DK2822300T3 (da) 2017-08-21
DE102013212853A1 (de) 2015-01-08

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