EP0071845B1 - Appareil pour la compensation des carences d'audition - Google Patents

Appareil pour la compensation des carences d'audition Download PDF

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Publication number
EP0071845B1
EP0071845B1 EP82106683A EP82106683A EP0071845B1 EP 0071845 B1 EP0071845 B1 EP 0071845B1 EP 82106683 A EP82106683 A EP 82106683A EP 82106683 A EP82106683 A EP 82106683A EP 0071845 B1 EP0071845 B1 EP 0071845B1
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EP
European Patent Office
Prior art keywords
filters
frequency
signal
amplifier
circuits
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.)
Expired
Application number
EP82106683A
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German (de)
English (en)
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EP0071845A2 (fr
EP0071845A3 (en
Inventor
Gerhard Heinrich Dr. Steeger
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.)
Siemens AG
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Siemens AG
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Application filed by Siemens AG filed Critical Siemens AG
Priority to AT82106683T priority Critical patent/ATE16748T1/de
Publication of EP0071845A2 publication Critical patent/EP0071845A2/fr
Publication of EP0071845A3 publication Critical patent/EP0071845A3/de
Application granted granted Critical
Publication of EP0071845B1 publication Critical patent/EP0071845B1/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
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • 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
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/356—Amplitude, e.g. amplitude shift or compression

Definitions

  • the invention relates to a device for compensating for hearing damage according to the preamble of claim 1.
  • Devices of this type are e.g. described in Scand. Audiol. 8: 121-126, 1979, as "programmable hearing aid with multichannel compression" by S. Mangold and A. Leijon (see in particular page 121, right column, last paragraph including page 122, right column, paragraph 4).
  • the electrical input signal which is generated, for example, in a microphone or an induction pick-up coil, is fed to a plurality of filters, which each pass adjacent sections of the offered frequency range.
  • the individual parts of the signal are then influenced with regard to the hearing loss that has to be compensated for by compression and change in the amplitudes.
  • the various signals from the so-called channels are brought together again and fed to the ear of the hearing impaired via an output converter.
  • the control of the filters as well as the compression and the volume control takes place via a memory that has been programmed with data about the hearing loss to be compensated or with data derived therefrom, for example by inputting this data through an audiometer via a data input of the hearing aid.
  • DE-A-2 707 607 relates to compensating filters which are also to be used in hearing aids and shows the use of discrete time filters.
  • the components required for this also result in the disadvantages of the arrangement according to US Pat. No. 3,784,750 because they result in a structure which is too bulky and which places high demands on the power supply.
  • US-A-4 185 168 discloses methods and devices with which approximately stationary noises can be filtered out of signals.
  • the construction required corresponds to the volume and power supply required discussed above with DE-A-2 707 607 and therefore has its disadvantages.
  • the invention has for its object to provide an arrangement for compensation for hearing damage according to the preamble of claim 1, which allows multi-channel processing of the input signal in terms of space and power consumption even in hearing aids to be worn on the head, which can be controlled from a memory .
  • the above object is achieved according to the invention by the measures mentioned in the characterizing part of claim 1.
  • Advantageous further developments and refinements can be found in the subclaims.
  • discrete-time and amplitude-analog filters eliminates the need for complex circuits, so that implementation in the size of commercially available pocket hearing aids or behind-the-ear hearing aids is made considerably easier.
  • time-discrete integrated filter circuits which have all the advantages of pure digital filters that are essential for hearing aid applications, but which no longer require analog-digital and digital-analog converters because of the analog representation of the state variables.
  • SCF switched capacitor filters
  • BBD chain storage filters
  • charge-CCD charge coupled devices
  • the filters mentioned can also be constructed in such a way that their coefficients can be changed very quickly by digital control signals it is possible according to the invention to carry out a multi-channel adaptive optimal filtering in the hearing device. At the same time, this enables the targeted reduction of interference noises, as is described in more detail in US Pat. No. 4,025,721.
  • the output signals from time-discrete filters operating in an amplitude-analog manner and from digital-to-analog converters are in the form of a staircase curve. This means that their spectrum contains repetitions of the signal spectrum at multiples of the sampling frequency (known e.g. from A.B. Carlson, Communication Systems, McGraw Hill, New York, 1968, Sect. 7.1 - 7.2, pages 272 to 289). If parts of these repetition spectra fall within the audible frequency range, they become audible as distortions. For this reason, these repetition spectra are usually suppressed by an analog low pass (a so-called “smoothing filter”).
  • an analog low pass a so-called “smoothing filter”.
  • the limit frequency is to be understood as the frequency at which a limit value of the frequency response (e.g. -60 dB) is finally undershot. In this way, the above-mentioned distortions can no longer be heard in a simple manner and there is no need for their screening.
  • the discrete-time filters used have the advantage that they can also be manufactured as integrated circuits using thick- or thin-film as well as monolithic integration technology. This enables highly complex circuits to be implemented in a small space.
  • the time-discrete mode of operation has the advantage that the problems with stability and temperature behavior known from integrated analog circuits can largely be avoided and thus also the circuits with discrete components which are often required to stabilize the integrated circuits.
  • Switch-capacitor filters in particular can be integrated particularly advantageously in complementary metal-oxide-silicon (CMOS) technology to form circuits which are characterized by a small space requirement, maximum time and temperature constancy, and very low supply voltages and currents.
  • CMOS complementary metal-oxide-silicon
  • the invention includes multi-channel hearing aids of any number of channels, i.e. Devices with generally n parallel frequency-selective filters, whose passband areas overlap at most slightly in the falling edges of the frequency response, n: s 2 being selected.
  • a desirable upper limit for the number of channels n at the current state of knowledge is the number of frequency groups (“critical bands”) of the hearing, which is given as 24 [according to E. Zwicker, Scaling, in: W.D. Keidel and W.D. Neff (Ed.), Handbook of Sensory Physiology, Vol. V, Part 2, Springer, Berlin 1975, section Ill. A, pages 409 to 4141.
  • the parameter memory of the programming circuit is expediently designed to be erasable, for example in the form of a programmable read-only memory erasable by ultraviolet light or electrical voltage [erasable programmable read-only memory (EPROM) or electrically alterable read-only memory (EAROM)].
  • EPROM erasable programmable read-only memory
  • EAROM electrically alterable read-only memory
  • An extension of the programming circuit which has proven to be expedient in many cases, can be obtained in that, in addition to the storage of predetermined basic data, the programming circuit itself enables the hearing aid data to be changed continuously, depending on the input signal, e.g. by implementing this circuit by means of a microcomputer circuit.
  • This enables adaptive interference signal suppression by means of optimal filtering, as is known from US Pat. No. 4,025,721.
  • the principle implemented there in only one channel can be expanded by the invention to multi-channel optimal filtering in all frequency channels.
  • a hearing aid equipped with filters according to the invention is drawn in a schematic block diagram.
  • a microphone 1 is provided as an input converter, which is connected to a preamplifier 2, which, as indicated by 2 ', has a low-pass frequency response.
  • the signal thus amplified is then divided at a point 3 to a plurality, i.e. a total of n time-discrete frequency filters 4a to 4n, distributed.
  • the one labeled 4a is a bandpass that passes frequencies from 50 to 600 Hz.
  • the filter 4b which is also connected to point 3, is a bandpass which is effective at frequencies from 0.6 to 2.5 kHz. If the frequency range of the filters 4a and 4b is reduced, several filters can then be provided, as indicated by points 4c.
  • the filter 4n follows, which is effective in the frequency distribution specified for 4a and 4b at 2.5 to approx. 8 kHz.
  • controllable amplifiers 5a and 5n which, together with controllers 6a to 6n, implement a gain control in a manner known in principle.
  • controllers 6a to 6n implement a gain control in a manner known in principle.
  • the arrangement of further control amplifiers is denoted by 5c and regulators by 6c.
  • the signals then reach controllable amplifiers 7a to 7n which, controlled by the output voltage of the volume control 8, adjust the volume.
  • the signals are then subjected to a peak value limitation in the nonlinear elements 9a to 9n in a known manner. Signal distortions caused thereby are reduced by post-filtering with filters 10a to 1 On, which frequency response can correspond to filters 4a to 4n, for example.
  • filters 10a to 1 On which frequency response can correspond to filters 4a to 4n, for example.
  • the limiters and the distortion-reducing filters 10a to 10n, 7c, 9c and 10c also indicate that additional channels can be added.
  • Filters 4a to 4n, controllers 6a to 6n and peak limiters 9a to 9n are set by a programming circuit 14. Filters 4a to 4n receive their control signals via lines 15a to 15n; The same applies to the controllers 6a to 6n via the lines 16a to 16n, to the limiters 9a to 9n via the lines 17a to 17n and finally to the filters 10a to 10n via the lines 18a to 18n.
  • the programming circuit 14 receives the setting data from an external device (e.g. an audiometer) via one or more data lines 19, the transmission and the storage in the programming circuit 14 being controlled via a plurality of control lines 20 from the external device.
  • the connection to the latter is mediated by a plug connection 21.
  • the programming circuit 14 is implemented by a microcomputer circuit, it can calculate the setting parameters completely or partially itself, depending on the input signal currently present, which is supplied to it for this purpose via the line 22.
  • the operation of the device results from the fact that in the input signal converter, i.e. in the microphone 1 or in its place induction pick-up coil for electromagnetic vibrations, generated electrical signal in the amplifier 2 is raised to such a voltage level that it is easily accessible to the subsequent signal processing.
  • the low-pass frequency response 2 ′ contained in the amplifier 2 prevents signal components and any interference signals that are coupled in, which are above half the sampling frequency, from being folded back into the audible frequency range during the sampling process to be carried out in the time-discrete filters 4a to 4n.
  • the signal in the filters 4a to 4n is then sampled and frequency-selectively suppressed to such an extent that the respective parts of the signal belonging to the specified frequency ranges can be treated separately.
  • the control amplifiers 5a to 5n which are controlled by the controllers 6a to 6n, a gain control that is dependent on the input or output level is achieved, whereby various known control principles can be used, for example the usual AGC circuits using the short-term average of these levels, but also instantaneous value compressors, as specified by Keidel and Spreng in DE-AS 1 512 720. This enables extensive compensation for disturbances in hearing dynamics (e.g. loudness compensation - recruitment).
  • the hearing aid wearer has the Possibility to bring the volume of the output signal into a volume range that is comfortable for him.
  • any nonlinear signal deformation can be achieved with the nonlinear circuits 9a to 9n.
  • a peak value limitation is carried out in a known manner and thus the occurrence of unpleasant or even hearing-damaging peak values of the output sound pressure level is prevented.
  • Filters 1 Oa to 1 On can be dispensed with if the interference suppression due to the low-pass properties of power amplifier 12 and receiver 13 is sufficient.
  • the further treatment of the sum signal takes place in the usual way, i.e. it is in the amplifier 12 to operate the output converter, i.e. in the present case, the receiver 13, brought the necessary intensity.
  • a signal then appears on the receiver 13 which is suitable for compensating for the particular hearing loss.
  • the controllers 6a to 6n must now be set so that the loss of dynamics in the respective frequency band is compensated for as well as possible, i.e. the controller 6n in the most high-frequency channel will bring about a significant gain reduction at high levels, while the controller 6a in the low-pass channel remains almost without influence.
  • the limiters 9a to 9n are to be set in a known manner in such a way that the patient's discomfort threshold is not appreciably exceeded by the signal level at any frequency. If the filters 10a to 10n are installed, they must be dimensioned in such a way that distortion components are largely suppressed (e.g. by designing them as duplicates of the corresponding channel separation filters 4a to 4n).
  • the programming circuit 14 represents a microcomputer circuit operating in the sense of an adaptive optimal filter, this will only maintain the basic setting described above if it is only in the input signal supplied via line 22 according to the methods described in US Pat. No. 4,025,721 Speech, but no significant interference signal components. However, if interference noise components are detected, the gain in each channel is automatically reduced the more the greater the ratio of interference level to speech signal level in the relevant channel in the sense of the optimal filter function.
  • the data which are supplied to the programming circuit 14 via the plug connection 21 can be sent to an external device, e.g. an audiometer.
  • an external device e.g. an audiometer.
  • the data transfer from the external device to the hearing aid can take place according to the signal plan of a standardized interface (e.g. CCITT-V.24 according to DIN 66020), only the signal levels have to be adjusted to the operating voltage of the hearing aid.
  • an agreed data word or control signal causes the non-volatile storage in an EPROM or EAROM. Later reprogramming is easily possible by deleting the non-volatile memory (EPROM or EAROM) according to its design (using ultraviolet radiation or electrical voltages) and transferring a new data record.

Landscapes

  • Acoustics & Sound (AREA)
  • Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • General Health & Medical Sciences (AREA)
  • Signal Processing (AREA)
  • Tone Control, Compression And Expansion, Limiting Amplitude (AREA)
  • Amplifiers (AREA)
  • Stereophonic System (AREA)
  • Filters That Use Time-Delay Elements (AREA)
  • Prostheses (AREA)
  • Cable Transmission Systems, Equalization Of Radio And Reduction Of Echo (AREA)

Claims (8)

1. Appareil pour compenser des défauts auditifs, dans lequel en série avec l'élément (1) recevant les signaux acoustiques d'entrée, se trouve prévu un montage parallèle formé de plusieurs branches de transmission de signaux, dont chacune est constituée respectivement par un filtre sélectif en fre- quence (4a à 4n), par un dispositif de régulation de l'amplification dépendant du niveau (6a à 6n et 7a à 7n), par un dispositif (9a à 9n) servant à réaliser une traitement non linéaire des signaux, et qui est suivi par un amplificateur de sommation (11) assemblant les signaux partiels et qui est relié par l'intermédiaire d'un amplificateur final (12) à un transducteur (13) de transmission des signaux de sortie, caractérisé par le fait que le filtre sélectif en fréquence (4a à 4n) ainsi qu'un filtre (10a à 1 On), qui peut être inséré en supplément au choix entre le dispositif (9a à 9n) servant à réaliser une traitement non linéaire du signal et l'amplificateur de sommation (11) et qui réduit les composantes de distorsion, produites par une influence non linéaire sur les signaux, du signal partiel respectif, sont réalisés sous la forme de filtres discrets dans le temps travaillant de façon analogique au niveau des amplitudes et formés par des circuits intégrés.
2. Appareil suivant la revendication 1, caractérisé par le fait que la fréquence d'horloge de travail des filtres discrets dans le temps (4a à 4n et 1 Oa à 1 On) est supérieure à la somme de la limite supérieure de fréquence de l'audibilité et de la fréquence limite supérieure de l'amplificateur d'entrée (2).
3. Appareil suivant la revendication 1, caractérisé par le fait que le dispositif comporte un circuit de programmation (14) qui est alimenté par l'intermédiaire d'une liaison (21 ) aboutissant à un appareil extérieur de production de données, par exemple un audiomètre, avec des données servant à influer sur les coefficients des filtres sélectifs en fréquence (4a à 4n), sur les paramètres des régulateurs d'amplification (6a à 6n) et sur les dispositifs non linéaires (9a à 9n) ainsi que sur les coefficients des filtres (10a à 10n) affaiblissants les distorsions.
4. Appareil suivant la revendication 1, caractérisé par le fait que les filtres sélectifs en fréquence (4a à 4n) et (10a à 10n) sont des filtres à condensateurs commutés («Switched Capacitor Filters»).
5. Appareil suivant la revendication 1, caractérisé par un microphone (1) utilisé en tant que transducteur de transmission de signaux d'entrée, un préamplificateur (2, 2') monté en aval, possédant une réponse en fréquence de filtre passe-bas et dont la sortie est raccordée à au moins deux (en général n) filtres discrets dans le temps et branchés en parallèle (4a à 4n), en aval desquels sont branchés, au moins dans un canal (en général dans l'ensemble des n canaux), respectivement un amplificateur de réglage (5a à 5n) comportant un régulateur (6a à 6n) servant à réaliser un réglage automatique de l'amplification (6a à 6n), un amplificateur de signaux (7a à 7n) dont l'amplification est modifiable par l'intermédiaire d'un régulateur commun (8) de l'intensité sonore, un élément non linéaire (9a à 9n) ainsi qu'un filtre sélectif en fréquence servant à réaliser l'affaiblissement ( Oa à 1 On) des composants de distorsion, et que les sorties de ces circuits parallèles sont raccordées à un point de sommation (11) auxquelles se trouvent raccordé un amplificateur terminal (12) et enfin un transducteur de sortie (13), ainsi que par un circuit de programmation (14) au moyen duquel les coefficients des filtres (4a à 4n et 10a à 1 On) et les paramètres des régulateurs (6a à 6n) ainsi que les linéarités (9a à 9n) sont réglables.
6. Appareil suivant la revendication 5, caractérisé par le fait que le circuit de programmation (14) peut être alimenté par des données de réglage en provenance d'un appareil externe, per l'intermédiaire de plusieurs lignes (19 et 20) et d'un connecteur (21).
7. Appareil suivant la revendication 6, caractérisé par le fait que le circuit de programmation (14) est un circuit de micro-ordinateur intégré.
8. Appareil suivant la revendication 7, caractérisé par le fait que des programmes et des données, qui permettent un réglage, dépendant du signal d'entrée appliqué au point (3) des filtres discrets dans le temps (4a à 4n), sont mémorisés et sont actifs dans le circuit du micro-ordinateur, tellement que bruitages sont affaiblié adaptifs.
EP82106683A 1981-08-06 1982-07-23 Appareil pour la compensation des carences d'audition Expired EP0071845B1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AT82106683T ATE16748T1 (de) 1981-08-06 1982-07-23 Geraet zur kompensation von gehoerschaeden.

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE3131193 1981-08-06
DE19813131193 DE3131193A1 (de) 1981-08-06 1981-08-06 Geraet zur kompensation von gehoerschaeden

Publications (3)

Publication Number Publication Date
EP0071845A2 EP0071845A2 (fr) 1983-02-16
EP0071845A3 EP0071845A3 (en) 1983-04-20
EP0071845B1 true EP0071845B1 (fr) 1985-11-27

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ID=6138766

Family Applications (1)

Application Number Title Priority Date Filing Date
EP82106683A Expired EP0071845B1 (fr) 1981-08-06 1982-07-23 Appareil pour la compensation des carences d'audition

Country Status (7)

Country Link
US (1) US4508940A (fr)
EP (1) EP0071845B1 (fr)
JP (1) JPS5834700A (fr)
AT (1) ATE16748T1 (fr)
CA (1) CA1198509A (fr)
DE (1) DE3131193A1 (fr)
DK (1) DK152869B (fr)

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DE3131193C2 (fr) 1989-04-13
EP0071845A2 (fr) 1983-02-16
US4508940A (en) 1985-04-02
ATE16748T1 (de) 1985-12-15
DE3131193A1 (de) 1983-02-24
CA1198509A (fr) 1985-12-24
JPS5834700A (ja) 1983-03-01
DK152869B (da) 1988-05-24
EP0071845A3 (en) 1983-04-20

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