EP2437521A1 - Procédé de compression fréquentielle à l'aide d'une correction harmonique et dispositif correspondant - Google Patents

Procédé de compression fréquentielle à l'aide d'une correction harmonique et dispositif correspondant Download PDF

Info

Publication number: EP2437521A1
Authority: EP; European Patent Office
Prior art keywords: frequency; harmonic; channel; shifted; channels
Prior art date: 2010-09-29
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

EP11178306A

Other languages

German (de)

English (en)

Other versions

EP2437521B2 (fr

EP2437521B1 (fr

Inventor

Robert BÄUML

Ulrich Kornagel

Thomas Pilgrim

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.)

2010-09-29

Filing date

2011-08-22

Publication date

2012-04-04

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2011-08-22 Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd

2012-04-04 Publication of EP2437521A1 publication Critical patent/EP2437521A1/fr

2014-04-30 Application granted granted Critical

2014-04-30 Publication of EP2437521B1 publication Critical patent/EP2437521B1/fr

2017-09-13 Publication of EP2437521B2 publication Critical patent/EP2437521B2/fr

Status Active legal-status Critical Current

2031-08-22 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; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
- H04R25/00—Electric hearing aids
- H04R25/35—Electric hearing aids using translation techniques
- H04R25/353—Frequency, e.g. frequency shift or compression
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; 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

Definitions

the present invention relates to a method of frequency-compressing an audio signal having a fundamental frequency and at least one harmonic by providing the audio signal in a plurality of frequency channels and shifting or mapping the harmonics of the audio signal from a first frequency channel of the plurality of frequency channels to a second frequency channel of the plurality of frequency channels.
the present invention relates to a corresponding device for frequency compression.
such a device can be used in a listening device.
a hearing device is understood here to be any sound-emitting device that can be worn in or on the ear, in particular a hearing device, a headset, headphones and the like.
Hearing aids are portable hearing aids that are used to care for the hearing impaired.
different types of hearing aids such as behind-the-ear hearing aids (BTE), hearing aid with external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (ITE), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
BTE behind-the-ear hearing aids
RIC hearing aid with external receiver
ITE in-the-ear hearing aids
ITE in-the-ear hearing aids
ITE 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 a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
the output transducer is usually used as an electroacoustic transducer, z. B. miniature speakers, or as an electromechanical transducer, z. B. bone conduction, realized.
the amplifier is usually integrated in a signal processing unit.
FIG. 1 shown using the example of a behind-the-ear hearing aid.
a hearing aid housing 1 for carrying behind the ear one or more microphones 2 for receiving the sound from the environment are installed.
a signal processing unit 3 which is also integrated in the hearing aid housing 1, processes the microphone signals and amplifies them.
the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal.
the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
the power supply of the hearing device and in particular the signal processing unit 3 is effected by a likewise integrated into the hearing aid housing 1 battery. 5
Dead regions are frequency ranges in which spectral components can no longer be audibly amplified.
FIG. 2 shows the principle of frequency compression by simply copying channels as it is already used for hearing aids.
the channel 14 ' (indicated by its center frequency 14) is copied to the channel 11' (indicated by its center frequency 11).
the channel 14 ' there is a tone 14 "(eg a harmonic) which is shifted to the tone 11" in the target channel 11'.
the pitch of the sound 14 "to the center frequency 14 is identical to the pitch of the sound 11" to the center frequency 11.
a harmonic correction occurs during or after the shifting or mapping of the harmonics into another frequency channel.
the harmonic is set to a frequency position, which is also an integer multiple of the fundamental frequency.
the harmonic represents a harmonic even after moving. This significantly reduces the artifacts.
the first frequency channel is completely shifted into the second frequency channel. This allows, for example, a frequency channel from a dead region in an audible range of a hearing aid wearer move. If there is a harmonic in the first frequency channel, then it is completely shifted with the frequency channel. Their distance from the center frequency of the channel remains unchanged.
One of the harmonics associated with the frequency channel may be estimated, and the shifted harmonic may then be further shifted to the first frequency in the second frequency channel. This means that the move takes place in two steps. First, the entire frequency channel is shifted and then within the frequency channel, the original harmonic is pushed back to a harmonic frequency position.
the further shifting to the first frequency in the second shift step can be effected, for example, by amplitude modulation. This can be realized in the time domain by a simple multiplication by a factor exp (j ⁇ ⁇ ⁇ t).
the harmonic in the first frequency channel represents a dominant frequency.
its position can be estimated relatively accurately before and after the shift.
the harmonic is mapped to the estimated first frequency by obtaining a signal synthetically generated in the second frequency channel, the amplitude of the harmonics in the first frequency channel, and the estimated frequency of the second frequency channel. It is therefore not necessary here to make a second shift step, for example by amplitude modulation, since a synthetic signal is used at the appropriate, harmonic point. However, this has the disadvantage that under some circumstances phase information is lost.
the inventive device for frequency compression has a signal processing device, which preferably has a polyphase filter bank. This makes it possible to generate only positive frequency components in the channels.
the device according to the invention is particularly advantageously used in a listening device and in particular in a hearing aid.
a frequency compression in hearing aid users can be realized with fewer artifacts.
FIG. 3 a frequency compression according to the prior art shown in detail.
frequencies are compressed according to a frequency mapping curve (eg, SPINC, BARK, ).
a frequency mapping curve eg, SPINC, BARK, .
the amplitude response a is plotted against the frequency f.
the line spectrum has numerous harmonics 20 which form the spectral fine structure of the harmonic signal.
the amplitudes of the harmonics 20 can be controlled by a spectral envelope 21 connect.
the distance f 0 between two harmonics 20 corresponds to the fundamental frequency in the entire spectral range.
the spectrum should now be compressed above a frequency f c .
Compression is channel-wise by copying selected channels of the original spectrum to lower-level channels.
the channels usually have a different bandwidth than the distance f 0 between the harmonics.
the harmonics 20 land when shifting to frequency positions outside the in FIG. 3 above shown line grid.
FIG. 3 below shows such a compressed spectrum.
the distances f 1 , f 2 between the individual lines 22, which represent the shifted harmonics, are no longer constant and in particular not equal to f 0 .
the envelope 23 of the compressed spectrum shows in the compressed region the shifted formands 24 and 25 as they originate from the original spectrum, the spacing of the lines 22 is uneven, thus destroying the spectral fine structure and thus the structure of the harmonic signal. Corresponding artifacts are the result.
the spectrum is compressed above the cutoff frequency f c .
the envelope 23 of the compressed spectrum has the same shape as that of FIG. 3 below. Ie. also the formands 24 and 25 can be seen in the compressed area.
the lines 26 of the spectrum in the compressed area above f c have each other the same distance f 0 as the lines or harmonics 20 in the uncompressed area. This means that the fine structure of the spectrum of the harmonic signal is unaffected by the compression. Accordingly, there are fewer artifacts.
the frequency structure of the harmonic raster of the uncompressed signal is estimated, ie the positions of the harmonics in the frequency domain are determined.
FIG. 5 this is explained in more detail above, which again shows a section of an uncompressed spectrum and below the section of a compressed spectrum.
the section of the displayed spectrum here has a line or harmonic 30. This lies in a frequency channel 31, which in turn has a center frequency f 31 .
Below the first frequency channel 31 is a second frequency channel 32, which has the center frequency f 32 .
the first frequency channel 31 is now shifted to the second frequency channel 32, copied or mapped. This represents a first step 33 of the frequency compression.
This step 33 corresponds to the compression according to the prior art of FIG.
the harmonic 30 of the first frequency channel 31 is pushed onto the line 34, which is assigned a frequency f 34 (also referred to as second frequency hereinafter).
the distance ⁇ f between the frequencies f 31 and f 30 is identical to the distance between the frequencies f 32 and f 34 .
the frequency f 34 does not correspond to a harmonic of the fundamental frequency. Rather, would be at the frequency position f 35 in the second frequency channel 32 is a harmonic. This can be determined, for example, by a first frequency estimate in the target frequency range, ie in the second frequency channel 32, to which the first frequency channel 31 is imaged or shifted.
the line 34 must therefore be shifted to the frequency f 35 in order to obtain the fine structure of the harmonic signal.
the frequency structure of the still uncorrected compressed spectral components is estimated in a second estimation.
the frequency f 34 of the line 34 is estimated or determined after the shift in the first step 33.
the frequency offset ie the distance between the frequencies f 34 and f 35 can be determined.
the offset is compensated by means of a modulation in a second step 36, whereby the harmonic raster is restored.
the line 34 is pushed to the frequency f 35 , resulting in the line 35 results.
the modulation can be achieved for example on the basis of the analytical signal by multiplication with a suitable complex rotational factor.
the shift by an angular frequency ⁇ 1 corresponds to a multiplication by the factor exp (j ⁇ ⁇ 1 ⁇ t).
the resulting modulation corresponds to an amplitude modulation.
this method can be used in a polyphase filter bank that generates only the complex-valued, analytical signal (only positive frequency component of a Fourier transformation) in the channels.
each channel can be cyclically modulated so that the frequency components in it are correspondingly cyclically shifted by the angular frequency ⁇ 1.
the above-described embodiment is based on actually shifting the harmonic 30 as a signal component of the audio signal.
the compressed spectral components are generated semi-synthetically.
the information about the frequency position of the semi-synthetically generated spectral components is obtained from the estimate of the uncompressed harmonic structure, ie the frequency 35 is determined as in the example above.
a synthetic signal is now generated.
the amplitude of this synthetic signal is adjusted to correspond to the amplitude of the original harmonic 30, ie the associated amplitude is obtained from the source spectrum. This also allows a frequency compression can be achieved in which the harmonic grid is maintained.
mapping rule of source frequency to target frequency for frequency compression is performed in audiology in a known manner.
the harmonic correction or compliance with the harmonic structure of the compressed spectral components is then achieved according to the invention.
the artefacts of the simple mapping rule according to the prior art are massively reduced.

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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)
Compression, Expansion, Code Conversion, And Decoders (AREA)
Stereophonic System (AREA)

EP11178306.4A 2010-09-29 2011-08-22 Procédé de compression fréquentielle à l'aide d'une correction harmonique et dispositif correspondant Active EP2437521B2 (fr)

Applications Claiming Priority (1)

Application Number	Priority Date	Filing Date	Title
DE102010041644.4A DE102010041644B4 (de)	2010-09-29	2010-09-29	Verfahren zur Frequenzkompression mit harmonischer Korrektur und Vorrichtung

Publications (3)

Publication Number	Publication Date
EP2437521A1 true EP2437521A1 (fr)	2012-04-04
EP2437521B1 EP2437521B1 (fr)	2014-04-30
EP2437521B2 EP2437521B2 (fr)	2017-09-13

Family

ID=44508965

Family Applications (1)

Application Number	Title	Priority Date	Filing Date
EP11178306.4A Active EP2437521B2 (fr)	2010-09-29	2011-08-22	Procédé de compression fréquentielle à l'aide d'une correction harmonique et dispositif correspondant

Country Status (6)

Country	Link
US (1)	US9258655B2 (fr)
EP (1)	EP2437521B2 (fr)
CN (1)	CN102436817B (fr)
AU (1)	AU2011226820B2 (fr)
DE (1)	DE102010041644B4 (fr)
DK (1)	DK2437521T4 (fr)

Families Citing this family (3)

* Cited by examiner, † Cited by third party
Publication number	Priority date	Publication date	Assignee	Title
TWI504282B (zh) *	2012-07-20	2015-10-11	Unlimiter Mfa Co Ltd	增加聽障者聽到聲音正確性之方法及助聽器
CN109741757B (zh) *	2019-01-29	2020-10-23	桂林理工大学南宁分校	用于窄带物联网的实时语音压缩和解压的方法
EP4391585A1 (fr) *	2022-12-19	2024-06-26	Nokia Technologies Oy	Appareil, procédés et programmes informatiques pour traitement audio

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DE2613513A1 (de) *	1976-03-30	1977-10-06	Albert Dipl Ing Kremer	Hoerhilfe insbesondere hoergeraet
US6577739B1 (en) *	1997-09-19	2003-06-10	University Of Iowa Research Foundation	Apparatus and methods for proportional audio compression and frequency shifting
WO2009143898A1 (fr) *	2008-05-30	2009-12-03	Phonak Ag	Procédé permettant l’adaptation du son par modification de fréquence dans une prothèse auditive, et prothèse auditive

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US4051331A (en) *	1976-03-29	1977-09-27	Brigham Young University	Speech coding hearing aid system utilizing formant frequency transformation
US4637402A (en) *	1980-04-28	1987-01-20	Adelman Roger A	Method for quantitatively measuring a hearing defect
FR2494988B1 (fr) †	1980-11-28	1985-07-05	Lafon Jean Claude	Perfectionnements aux dispositifs de prothese auditive
JP2884163B2 (ja) †	1987-02-20	1999-04-19	富士通株式会社	符号化伝送装置
US5285144A (en) *	1988-09-02	1994-02-08	Board Of Regents, The University Of Texas System	Generation of multi-phase multiple-order harmonics of a fundamental frequency source with adjustable phase angle capability
AT398670B (de) †	1991-11-13	1995-01-25	Viennatone Gmbh	Verfahren zur verschiebung der frequenz von signalen
US5864813A (en) †	1996-12-20	1999-01-26	U S West, Inc.	Method, system and product for harmonic enhancement of encoded audio signals
US7003120B1 (en) *	1998-10-29	2006-02-21	Paul Reed Smith Guitars, Inc.	Method of modifying harmonic content of a complex waveform
AU2002300314B2 (en) †	2002-07-29	2009-01-22	Hearworks Pty. Ltd.	Apparatus And Method For Frequency Transposition In Hearing Aids
US7248711B2 (en) *	2003-03-06	2007-07-24	Phonak Ag	Method for frequency transposition and use of the method in a hearing device and a communication device
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DK1920632T3 (da) *	2005-06-27	2010-03-08	Widex As	Høreapparat med forbedret højfrekvensgengivelse og fremgangsmåde til at behandle et lydsignal
EP1742509B1 (fr) †	2005-07-08	2013-08-14	Oticon A/S	Système et procédé pour éliminer le bruit feed-back dans un dispositif auditif
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US8019431B2 (en) †	2008-06-02	2011-09-13	University Of Washington	Enhanced signal processing for cochlear implants
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2010
- 2010-09-29 DE DE102010041644.4A patent/DE102010041644B4/de active Active
2011
- 2011-08-22 DK DK11178306.4T patent/DK2437521T4/en active
- 2011-08-22 EP EP11178306.4A patent/EP2437521B2/fr active Active
- 2011-09-22 AU AU2011226820A patent/AU2011226820B2/en not_active Ceased
- 2011-09-28 CN CN2011102959103A patent/CN102436817B/zh active Active
- 2011-09-29 US US13/248,157 patent/US9258655B2/en active Active

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number	Priority date	Publication date	Assignee	Title
DE2613513A1 (de) *	1976-03-30	1977-10-06	Albert Dipl Ing Kremer	Hoerhilfe insbesondere hoergeraet
US6577739B1 (en) *	1997-09-19	2003-06-10	University Of Iowa Research Foundation	Apparatus and methods for proportional audio compression and frequency shifting
WO2009143898A1 (fr) *	2008-05-30	2009-12-03	Phonak Ag	Procédé permettant l’adaptation du son par modification de fréquence dans une prothèse auditive, et prothèse auditive

Also Published As

Publication number	Publication date
DK2437521T4 (en)	2017-12-18
DE102010041644B4 (de)	2019-07-11
DE102010041644A1 (de)	2012-03-29
AU2011226820B2 (en)	2013-10-03
EP2437521B2 (fr)	2017-09-13
US20120076332A1 (en)	2012-03-29
AU2011226820A1 (en)	2012-04-12
EP2437521B1 (fr)	2014-04-30
CN102436817B (zh)	2013-10-30
DK2437521T3 (da)	2014-08-11
US9258655B2 (en)	2016-02-09
CN102436817A (zh)	2012-05-02

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