EP2519033A2 - Procédé de fonctionnement d'un appareil auditif avec perception réduite de filtrage en peigne et appareil auditif avec perception réduite de filtrage en peigne - Google Patents

Procédé de fonctionnement d'un appareil auditif avec perception réduite de filtrage en peigne et appareil auditif avec perception réduite de filtrage en peigne Download PDF

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Publication number
EP2519033A2
EP2519033A2 EP12162979A EP12162979A EP2519033A2 EP 2519033 A2 EP2519033 A2 EP 2519033A2 EP 12162979 A EP12162979 A EP 12162979A EP 12162979 A EP12162979 A EP 12162979A EP 2519033 A2 EP2519033 A2 EP 2519033A2
Authority
EP
European Patent Office
Prior art keywords
hearing aid
hearing
operating
acoustic signal
phase
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
EP12162979A
Other languages
German (de)
English (en)
Other versions
EP2519033A3 (fr
EP2519033B1 (fr
Inventor
Sebastian Pape
Ronny Hannemann
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
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2519033A2 publication Critical patent/EP2519033A2/fr
Publication of EP2519033A3 publication Critical patent/EP2519033A3/fr
Application granted granted Critical
Publication of EP2519033B1 publication Critical patent/EP2519033B1/fr
Active legal-status Critical Current
Anticipated expiration legal-status Critical

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • H04R25/305—Self-monitoring or self-testing
    • 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
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R5/00—Stereophonic arrangements
    • H04R5/033—Headphones for stereophonic communication
    • 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
    • H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
    • 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
    • H04R2225/61—Aspects relating to mechanical or electronic switches or control elements, e.g. functioning
    • 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
    • H04R2460/07—Use of position data from wide-area or local-area positioning systems in hearing devices, e.g. program or information selection
    • 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
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/603—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of mechanical or electronic switches or control elements
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04S—STEREOPHONIC SYSTEMS 
    • H04S7/00—Indicating arrangements; Control arrangements, e.g. balance control
    • H04S7/30—Control circuits for electronic adaptation of the sound field
    • H04S7/302—Electronic adaptation of stereophonic sound system to listener position or orientation
    • H04S7/303—Tracking of listener position or orientation

Definitions

  • the present invention relates to a method of operating a hearing aid with reduced comb filter perception. Moreover, the present invention relates to a hearing aid with reduced comb filter perception.
  • a hearing aid is used to supply a hearing-impaired person with acoustic ambient signals that are processed and amplified for compensation or therapy of the respective hearing impairment. It comprises in principle one or more input transducers, a signal processing device with an amplifying device or an amplifier and an output transducer.
  • the input transducer is typically a sound receiver, e.g. a microphone, and / or an electromagnetic receiver, e.g. an induction coil.
  • the output transducer is typically used as an electroacoustic transducer, e.g. a miniature speaker, or as an electromechanical transducer, e.g. a bone conduction listener, realized. He is also referred to as a handset or receiver.
  • the output transducer generates output signals that are routed to the patient's ear and produce a hearing sensation in the patient.
  • the amplifier is usually integrated in the signal processing device.
  • the power supply of the hearing aid is effected by a battery arranged in the hearing aid housing.
  • the essential electronic components of a hearing aid are usually arranged on a printed circuit board as a circuit carrier or connected thereto.
  • CiC hearing aids Completely-in-Canal are similar to the IdO hearing aids, but are fully worn in the ear canal.
  • RiC-BtE hearing aids In BTE hearing aids (behind-the-ear, behind the ear), a housing with components such as battery and signal processing equipment is worn behind the ear and a flexible sound tube, also referred to as a tube, directs the acoustic output signals of a receiver from the housing to the ear canal
  • RiC-BtE hearing aids (receiver-in-canal behind-the-ear) are similar to BTE hearing aids, but the receiver is worn in the ear canal and instead of a sound tube, which conducts acoustic signals to an earpiece, conducts a flexible cable, also called Earpiece or handset connection means electrical signals to a receiver which is attached to the front of the cable.
  • Hearing aids generally have an ear piece which, in the case of a BTE hearing aid, is located at the end of the sound tube and, in the case of an RIC BTE hearing aid, near the receiver and is inserted into the ear canal.
  • the housing or parts thereof may take over the function of the earpiece.
  • Open earpieces which are essentially intended to keep the sound tube or tube with the earpiece centered in the ear canal, are generally more comfortable in terms of wearing comfort because they put less pressure on the ear canal and allow for better venting of the ear canal.
  • Acoustically open ear pieces have the advantage that the possible pressure equalization in the ear canal closure effects, such as an unnatural-sounding own voice or transmitted through structure-borne Kaugehoffsche be avoided.
  • a disadvantage of the first method is that the information content of the useful signal is limited by the filtering.
  • a disadvantage of the use of closed ear pieces is, compared to open ear pieces, poorer comfort and possible closure effects.
  • the object of the present invention is therefore to specify a method for operating a hearing device with reduced comb filter perception. Furthermore, the object of the invention is to provide a hearing aid with reduced comb filter perception.
  • the invention solves this problem with a method for operating a hearing aid having the features of the first independent patent claim and a hearing aid having the features of the second independent claim.
  • the basic idea of the invention is a method for operating a hearing device, in which a head movement of a hearing aid wearer is detected and, in the case of a detected head movement, an acoustic signal detected with a microphone is amplified and output in phase modulated form with a receiver.
  • This technique uses a natural ability of the human brain to block out comb filter effects so that they are not consciously perceptible.
  • humans are exposed to sound situations in which comb filter effects are also formed. If, for example, music is output in a room via a loudspeaker, the sound is reflected on the walls and reaches the ears of a listener with a time delay to direct sound. The occurring comb filter are measurable, but are not consciously perceived by the listener. It is believed that the human brain is able to integrate and thus eliminate sound impressions of both ears over time and in the frequency domain.
  • the human constantly performs small, sometimes smallest head movements, which cause on the one hand, that the characteristic, ie the amplitude response, the comb filter constantly varies and, secondly, that the phase of the acoustic signals that hit the right and left ear, constantly varied.
  • the human brain is able to wipe out comb filter effects.
  • an acoustic signal which has been subjected to a comb filter is supplied directly to the ear, as is the case, for example, when using a hearing aid, comb filter effects can be heard.
  • the inventive method solves this problem in that the head movement of a hearing aid wearer, for example by evaluation an output signal of an acceleration sensor, which is arranged on or in the hearing aid and thus experiences the same accelerations as the head is monitored.
  • the phase, ie the delay, of the acoustic signal detected and amplified by a microphone is constantly varied, ie a phase modulation of the hearing aid signal takes place.
  • These small variations in the amplified hearing aid signal simulate the natural effect that allows the human brain to block out comb filter effects.
  • the variations in the phase position of the hearing aid signal that are performed during the detection of head movements lead to a variation of the comb filter characteristic, whereby the perception of the comb filter effects is reduced.
  • an acoustic signal and an acceleration value of the hearing device are detected, for example with a microphone of a hearing device.
  • the detection of the acceleration value can be achieved, for example, by an acceleration sensor, can be measured by the linear accelerations, or by a gyrosensor, by the rotational movements and accelerations are measurable carried out, wherein the acceleration sensor can be arranged for example in the hearing aid. Accelerations are interpreted as head movements. If the linear and / or the rotational acceleration value is greater than a threshold value, the detected acoustic signal is subjected to a phase modulation, that is, the output of the acoustic signal in a later method step is delayed.
  • the threshold value can be given in the unit m / s 2 in the case of a linear acceleration sensor, and in the unit ° / s 2 in the case of a rotary acceleration sensor.
  • the threshold is obtained by series of measurements with subjects, such as the threshold corresponding to, for example, the average of the acceleration sensor signals instructing the subjects to keep their heads steady.
  • the detected acoustic signal is amplified and output, taking into account the optionally modulated in the previous step phase on a receiver of the hearing aid. If an abort criterion is not met, the first step is jumped.
  • the termination criterion can be, for example, the switching state "off" of an on-off switch on the hearing aid.
  • the modulated phase is modulated by a noise function.
  • noise function i. a function with a wide nonspecific frequency spectrum
  • the change in phase is uncorrelated.
  • the modulated phase is modulated between 0 and 10 ms.
  • a positive correlation in this context means that a large output signal of the motion sensor causes a large amplitude of the phase modulation.
  • the method in the individual hearing aids is preferably carried out independently of one another.
  • a hearing device with a hearing device housing, at least one microphone, a receiver, an earpiece, a power supply unit and a signal processing unit, which comprises at least one motion sensor which is connected to the signal processing unit, wherein head movements of the hearing device wearer can be detected by the motion sensor and wherein the signal processing unit comprises means for modulating, upon detection of head movements of the hearing device wearer, the phase of an acoustic signal detectable by the microphone and amplifiable by the signal processing unit and deliverable by the receiver.
  • the hearing aid according to the invention comprises as further component at least one motion sensor which can detect head movements of the hearing aid wearer and relay them in the form of measurement signals to the signal processing unit.
  • the signal processing unit such as an electronic computer or microcontroller, receives the motion sensor signals and is capable of modulating the phase of the acoustic signals detected by the microphone.
  • the signal processing unit of the hearing aid comprises means for carrying out one of the methods described above.
  • the motion sensor comprises at least one acceleration sensor and / or at least one gyrosensor.
  • An acceleration sensor measures the acceleration by determining the inertial force acting on a test mass.
  • miniaturized sensors are often used whose measuring principle is based on piezoelectric effects.
  • Other acceleration sensors are designed as so-called micro-electro-mechanical systems, MEMS. They are available in versions for measuring linear accelerations or for measuring angular accelerations.
  • the motion sensor comprises at least two acceleration sensors and / or at least two gyro sensors which are arranged in non-parallel axes, in particular in mutually orthogonally oriented axes.
  • Two or more acceleration sensors which may also be components of an acceleration sensor component, allow the measurement of acceleration vectors in a two- or three-dimensional space.
  • the prerequisite for this is that the measuring direction of the acceleration sensors is not parallel.
  • For the measurement of a spatial acceleration vector it is favorable to align the measuring directions orthogonal to one another. The same applies to the measurement of angular acceleration vectors in a two- or three-dimensional space.
  • FIG. 1 schematically shows a behind-the-ear hearing aid 1 'according to the prior art. It comprises a housing 2 'to be supported behind the auricle 12' of a hearing device wearer with a hearing device wearing hook 5 '.
  • a signal processing unit 9' In the housing 2 ', in addition to electronic components, which are combined to form a signal processing unit 9', a microphone 3 ', a battery 8' and a receiver 4 'are arranged.
  • the acoustic signal generated by the receiver 4 ' is passed through the hearing device wearing hook 5' and a sound tube 6 'to an earpiece 7', which is inserted into an auditory canal 13 'of the hearing aid wearer.
  • a control element 10' On the hearing aid housing 2 ', a control element 10', for example an on-off switch or a Radiomoduseinstellregler, arranged, which is connected to the signal processing unit 9 '.
  • FIG. 2 an example of a frequency response 20 of a comb filter is shown. It shows the course of the amplitude 22, eg in decibels, above the frequency 21, eg in Hertz.
  • Characteristic of a comb filter are the filter frequencies 24, also called notches, which occur several times and have the same frequency spacing 23. Between the filter frequencies 24, the gain increases up to the maxima 25, so that the comb-shaped amplitude curve 20, which gave this filter its name, results.
  • FIG. 3 shows an embodiment of a flowchart of a method 100 according to the invention.
  • the first method step 101 an acoustic signal and an acceleration value of the hearing device are detected, for example with a microphone of a hearing aid. Accelerations are interpreted as head movements.
  • query 102 is performed as to whether the linear and / or the rotational acceleration value are greater than a threshold value.
  • the threshold value is, for example, equal to the acceleration value with a quiet posture of the head. If the query 102 is satisfied, the detected acoustic signal is subjected to a phase modulation in method step 103, that is, the output of the acoustic signal is delayed in one of the following method steps.
  • the phase of the detected acoustic signal is not changed.
  • the detected acoustic signal is amplified and output, taking into account the optionally modulated in the previous method step phase via a receiver of the hearing aid.
  • query 105 is made as to whether an abort criterion has been met.
  • the termination criterion can be, for example, the switching state "off" of an on-off switch on the hearing aid. Another termination criterion would be, for example, a change of the operating mode of the hearing aid. If the abort criterion is met, the method ends, otherwise the first method step 101 is jumped.
  • FIG. 4 is an example of a phase curve 40 according to the invention over time 41, for example in milliseconds, shown, wherein the phase 42 is given for example in milliseconds.
  • the phase 46 is zero in the time ranges 45, ie no additional delay is added to the delay of the signal output inherently caused by the signal processing unit of the hearing aid.
  • a phase modulation such as a noise function, applied.
  • FIG. 5 an embodiment of a hearing aid 1 according to the invention is shown schematically. It comprises a housing 2 to be worn behind the auricle 12 of a hearing aid wearer with a hearing device wearing hook 5.
  • a microphone 3 In the housing 2, a microphone 3, a battery 8 and a receiver 4 are arranged in addition to electronic components that are combined to form a signal processing unit 9.
  • the acoustic signal generated by the receiver 4 is passed through the hearing device wearing hook 5 and a sound tube 6 to an earpiece 7, which is inserted into an auditory canal 13 of the hearing aid wearer.
  • a control element 10 for example, an on-off switch or a Radioactive switch
  • the hearing device 1 comprises a motion sensor 11, which is arranged in or on the hearing device housing 2 and, in the worn state of the hearing device 1, is exposed to the same accelerations as the head of the hearing device wearer.
  • the motion sensor 11 includes, for example, three acceleration sensors that are orthogonal to each other and measure accelerations in the direction of the coordinate axes 16.
  • the motion sensor 11 may include three gyro sensors that measure angular accelerations in the directions 15.

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  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Health & Medical Sciences (AREA)
  • Signal Processing (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Neurosurgery (AREA)
  • Headphones And Earphones (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Gyroscopes (AREA)
  • Soundproofing, Sound Blocking, And Sound Damping (AREA)
  • Manipulator (AREA)
EP12162979.4A 2011-04-29 2012-04-03 Procédé de fonctionnement d'un appareil auditif avec perception réduite de filtrage en peigne et appareil auditif avec perception réduite de filtrage en peigne Active EP2519033B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102011075006A DE102011075006B3 (de) 2011-04-29 2011-04-29 Verfahren zum Betrieb eines Hörgerätes mit verringerter Kammfilterwahrnehmung und Hörgerät mit verringerter Kammfilterwahrnehmung

Publications (3)

Publication Number Publication Date
EP2519033A2 true EP2519033A2 (fr) 2012-10-31
EP2519033A3 EP2519033A3 (fr) 2016-04-20
EP2519033B1 EP2519033B1 (fr) 2017-12-13

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EP12162979.4A Active EP2519033B1 (fr) 2011-04-29 2012-04-03 Procédé de fonctionnement d'un appareil auditif avec perception réduite de filtrage en peigne et appareil auditif avec perception réduite de filtrage en peigne

Country Status (5)

Country Link
US (1) US8873781B2 (fr)
EP (1) EP2519033B1 (fr)
CN (1) CN102761815B (fr)
DE (1) DE102011075006B3 (fr)
DK (1) DK2519033T3 (fr)

Cited By (2)

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Publication number Priority date Publication date Assignee Title
EP3340656A1 (fr) * 2016-12-22 2018-06-27 Sivantos Pte. Ltd. Procédé de fonctionnement d'un dispositif de correction auditive
EP2908550B1 (fr) 2014-02-13 2018-07-25 Oticon A/s Dispositif de prothèse auditive comprenant un élément de capteur

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KR102192361B1 (ko) * 2013-07-01 2020-12-17 삼성전자주식회사 머리 움직임을 이용한 사용자 인터페이스 방법 및 장치
KR102021780B1 (ko) * 2013-07-02 2019-09-17 삼성전자주식회사 보청기 및 보청기 제어 방법
US9048798B2 (en) 2013-08-30 2015-06-02 Qualcomm Incorporated Gain control for a hearing aid with a facial movement detector
DE102017202480A1 (de) 2017-02-16 2018-08-16 Sivantos Pte. Ltd. Verfahren zum Betrieb einer Hörvorrichtung und Hörvorrichtung
DE102018206979A1 (de) 2018-05-04 2019-11-07 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts und Hörgerät
DE102018207780B3 (de) 2018-05-17 2019-08-22 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgerätes
DE102018209801A1 (de) * 2018-06-18 2019-12-19 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörvorrichtungssystems und Hörvorrichtungssystem

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Publication number Priority date Publication date Assignee Title
EP2908550B1 (fr) 2014-02-13 2018-07-25 Oticon A/s Dispositif de prothèse auditive comprenant un élément de capteur
US10524061B2 (en) 2014-02-13 2019-12-31 Oticon A/S Hearing aid device comprising a sensor member
US11128961B2 (en) 2014-02-13 2021-09-21 Oticon A/S Hearing aid device comprising a sensor member
US11533570B2 (en) 2014-02-13 2022-12-20 Oticon A/S Hearing aid device comprising a sensor member
US11889265B2 (en) 2014-02-13 2024-01-30 Oticon A/S Hearing aid device comprising a sensor member
EP3340656A1 (fr) * 2016-12-22 2018-06-27 Sivantos Pte. Ltd. Procédé de fonctionnement d'un dispositif de correction auditive
US10652670B2 (en) 2016-12-22 2020-05-12 Sivantos Pte. Ltd. Method for operating a hearing aid and hearing aid

Also Published As

Publication number Publication date
DE102011075006B3 (de) 2012-10-31
DK2519033T3 (da) 2018-03-05
US8873781B2 (en) 2014-10-28
US20120275630A1 (en) 2012-11-01
EP2519033A3 (fr) 2016-04-20
CN102761815A (zh) 2012-10-31
CN102761815B (zh) 2017-03-01
EP2519033B1 (fr) 2017-12-13

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