EP0793897A1 - Hearing aid - Google Patents
Hearing aidInfo
- Publication number
- EP0793897A1 EP0793897A1 EP95921771A EP95921771A EP0793897A1 EP 0793897 A1 EP0793897 A1 EP 0793897A1 EP 95921771 A EP95921771 A EP 95921771A EP 95921771 A EP95921771 A EP 95921771A EP 0793897 A1 EP0793897 A1 EP 0793897A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- signal
- hearing aid
- low
- input
- clock
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
- 230000006870 function Effects 0.000 claims description 7
- 230000005540 biological transmission Effects 0.000 claims description 4
- 230000001360 synchronised effect Effects 0.000 claims description 3
- 230000008054 signal transmission Effects 0.000 abstract 1
- 230000003321 amplification Effects 0.000 description 3
- 238000003199 nucleic acid amplification method Methods 0.000 description 3
- 230000006835 compression Effects 0.000 description 2
- 238000007906 compression Methods 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 238000005516 engineering process Methods 0.000 description 2
- 230000010354 integration Effects 0.000 description 2
- 206010011878 Deafness Diseases 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 230000001419 dependent effect Effects 0.000 description 1
- 238000005265 energy consumption Methods 0.000 description 1
- 230000010370 hearing loss Effects 0.000 description 1
- 231100000888 hearing loss Toxicity 0.000 description 1
- 208000016354 hearing loss disease Diseases 0.000 description 1
- 238000001208 nuclear magnetic resonance pulse sequence Methods 0.000 description 1
- 238000001228 spectrum Methods 0.000 description 1
- 230000007704 transition Effects 0.000 description 1
- 238000002604 ultrasonography Methods 0.000 description 1
- 238000011144 upstream manufacturing Methods 0.000 description 1
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
Definitions
- the invention relates to a hearing aid with a microphone, a transmission part for signal processing and an output amplifier with a receiver connected to it.
- Output amplifiers for hearing aids should have low energy consumption in addition to low distortion, even with high output power.
- Class B amplifiers are more efficient than A amplifiers.
- Amplifiers of this type have also hitherto been customary in hearing aids.
- D-amplifiers are, for example. in European Patent Application o 590 903 AI from Exar Corporation and in US Pat. Nos. 5, 247,581 to Exar Corporation and US Pat. Nos. 4,689,819 and 4,592,087 to Industrial Research Products Inc. disclosed and described in detail.
- the rectangular pulse sequence of an oscillator which is in the ultrasound range, is fed to an integrator, which is also fed the output voltage of a low-frequency signal, which arrives from a microphone via an amplifier train and serves as a bias voltage.
- the output signal of the integrator is then a triangular pulse train, the zero crossings through which Integrator supplied bias lying in the hearing frequency range can be varied. I.e. , this low-frequency bias voltage shifts the zero crossings of the triangular signal from a course symmetrical to the axis of symmetry without bias signal to asymmetrical conditions, the asymmetry in terms of sign and size being a continuously changing function of the amplitude of the low-frequency input signal.
- Such D-amplifiers working with pulse width modulation have a very good efficiency and have almost no cross modulation.
- a disadvantage of the D-amplifier with pulse width modulation is that the pulse width should be changed either continuously or in very small steps if a high signal to noise ratio is to be achieved.
- the known class D output amplifiers use continuous modulation, i.e. a continuous variation of the pulse width and therefore require a continuous output signal from the microphone as an input signal. If the signal processing preceding the output amplifier is time-discrete and / or amplitude-discrete, then this digital signal must first e.g. be converted into a network or a digit / analog converter. This represents an unreasonable additional effort.
- the invention is therefore intended to propose a hearing aid with a novel, considerably simpler output amplifier, in which a relatively high signal / noise ratio can be achieved, with extremely low power requirements and high output power, with minimal distortion and any lack of cross modulation and a possible control of the output signal with a digital or an analog input signal.
- the output amplifier can be constructed completely as a digitally highly integrated CMOS circuit.
- Fig. 1 shows a basic circuit diagram of a hearing aid with an output amplifier according to the invention
- Fig. 2 a Signa icon converter used in the output amplifier of the hearing aid
- Output amplifier of the hearing aid. 1 shows, for example, a hearing aid device with a novel output amplifier, the use of which is not limited to the use in hearing aid devices, but is generally applicable to digital amplifiers where a high ratio of useful signal to interference signal is important.
- the acoustic signal is picked up by a microphone 1 and limited in a low-pass filter as an anti-aliasing filter to a frequency range customary in hearing aids.
- This low-frequency signal is now subjected to signal processing in a signal processor 3.
- the analog input signal is either further processed analogously in such a way that the amplifier characteristic of the signal processor is adapted to the variables required for the respective hearing damage or hearing loss of its wearer with respect to all the variables.
- Such variable which are dependent on the frequency, are, for example. the amplification of the individual stages, the limit level, the compression threshold, the automatic amplification control with its response and decay times, a combination of compression and expansion or a non-linear course of the amplification of individual stages or all stages in total, as well as the output switching Pressure level.
- the signal processor on the input side would have to contain a digital-analog log converter, for which a separate clock generator would be required for the clock.
- a new output amplifier then follows the Signal processor 3.
- This consists essentially of a signal converter 4, which is essentially a is.
- This signal converter first contains a subtractor stage 5 with two inputs, namely a positive input and a negative input, the positive input being connected to the output of the signal processor 3.
- This subtraction stage 5 is followed by a low-pass filter 6.
- the low-pass filter 6 could be an integrator.
- a comparison stage 7 with a holding network is connected to this integrator 6.
- the output of this comparison stage is connected via a feedback connection to the negative input of the subtraction stage 5.
- a high-frequency clock generator 8 is provided, which sends a high-frequency clock pulse signal with a frequency in the range of approximately 1 MHz to the comparison stage
- the output of the Signa Ikon age 4 is connected to the receiver 10 via a low-pass function.
- a clock generator with a significantly lower frequency required for the signal processor 3 is preferably provided by the high-frequency clock generator
- a typical clock frequency for the signal processor 3 could be about 32 kHz.
- the high-frequency clock signal 11 of the clock generator 8 is fed to the comparison stage 7.
- the digital input signal 12 in FIG. 3 (an extremely simplified representation) is fed to the subtraction stage at its positive input.
- the output signal 14 of the signal converter 4 reaches the negative input of the subtraction stage via a feedback connection and is subtracted there from the input signal 12.
- the resulting output signal is fed to the integrator 6 (which represents the low-pass filter here) and integrated there to form the output signal 13.
- This signal 13 is converted in the comparison stage 7 with holding network synchronously with the edges of the high-frequency clock signal into the output signal 14, which has only two possible values, which for the sake of simplicity are shown here as +1 and -1.
- the input signal 12 should initially have the value -0.5.
- the integrated signal 13 then rises from -1.5 to zero, which results in a first output pulse transition from -1 to +1.
- the integrated signal then drops again to -1, 5, after which the output signal 14 again assumes the value -1.
- the subsequent rise in the input signal 12 to the value zero results in a steeper rise in the integrated signal 13 to the value 0.5.
- the corresponding signal values of the output signal 14 between -1 and +1 are then obtained via the integration, the values -1 corresponding to the lower value of the integrated signal and the values +1 to the upper value of the integrated signal .
- the further values of the input signal of 0.3, 0.6 and 1.0 are converted into corresponding pulses of the output signal 14 via the integration. I.e. in the output signal 14 the ratio of positive values to negative values per time unit changes depending on the input signal 12.
- the analog signal When converting a low-frequency analog signal into a digital signal by time-discrete and / or amplitude-discrete conversion, the analog signal is quantized.
- the stages of the input signal 12 shown in FIG. 3 therefore represent corresponding amplitude steps of a quantized analog signal.
- clock pulse frequencies of z. B. 100 kHz is sufficient, in the present case, to achieve a large ratio of useful signal to interference signal, significantly higher clock pulse frequencies are required, which can be, for example, in the range of 1 MHz.
- the output signal 14 of the signal converter 4 contains, in addition to the desired amplified low-frequency component, a strong high-frequency signal component which, of course, represents an undesired interference signal which, for example, must be removed by a passive low-pass filter.
- this output amplifier is used in a hearing aid, then the inductance of the voice coil of the listener and the low-pass properties of the mechanical and acoustic system of the hearing aid and the human ear can take over this low-pass function completely, so that a separate low-pass filter appears to be unnecessary.
- This novel output amplifier which is particularly suitable for hearing aids, has a number of advantages. All pulse edges are synchronized with a known clock pulse frequency, which can also be used to synchronize the clock pulse generator required for the upstream signal processor, which operates at a significantly lower clock frequency.
- the input signal of the output amplifier can be a digital signal and the output amplifier can be designed as a pure digital circuit. Ie. but that the entire circuit can be constructed as a digital circuit, an analog / digital converter only having to be provided at the input of the signal processor 3. This results in the further possibility of building up the entire circuit using C-MOS technology as a highly integrated circuit.
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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)
- Amplifiers (AREA)
- Adornments (AREA)
- Finger-Pressure Massage (AREA)
- Compression, Expansion, Code Conversion, And Decoders (AREA)
Abstract
Described is a hearing aid with a microphone (1), a signal-transmission unit (2, 3) for forming or otherwise processing the signal, an output amplifier (4) to which an earphone (10) is connected, and a battery as the power supply. The output amplifier (4) is designed essentially as a Σ-Δamplifier and is connected to a pulse generator (8) which produces a high-frequency pulsed signal in the 1 MHz region as well as a series-connected low-pass filter (15). The input signal to the signal converter is a representation, produced by signal processing, of the low-frequency input signal to the hearing aid, this signal being converted in the signal converter into a signal which can have only two possible values. The output signal (14) thus appears, after passing through the low-pass filter, essentially as an amplified copy of the low-frequency input signal.
Description
Hörhilfsgerät Hearing aid
Die Erfindung betrifft ein Hörhilfsgerät mit einem Mikrofon, einem Übertra¬ gungsteil zur Signal Verarbeitung und einem Ausgangsverstärker mit daran an¬ geschlossenem Hörer.The invention relates to a hearing aid with a microphone, a transmission part for signal processing and an output amplifier with a receiver connected to it.
Ausgangsverstärker für Hörhilfsgeräte sollten neben geringen Verzerrungen einen geringen Energiebedarf, selbst bei hoher Ausgangsleistung, aufweisen .Output amplifiers for hearing aids should have low energy consumption in addition to low distortion, even with high output power.
K lasse- B-Verstärker haben einen besseren Wirkungsgrad als A- Verstärker . Verstärker dieser Art sind bei Hörgeräten auch bisher üblich gewesen .Class B amplifiers are more efficient than A amplifiers. Amplifiers of this type have also hitherto been customary in hearing aids.
Ausgangsverstärker in Form von Schaltverstärkern haben einen noch besseren Wirkungsgrad, da die Verluste in den Schaltern theoretisch Null sein können .Output amplifiers in the form of switching amplifiers are even more efficient because the losses in the switches can theoretically be zero.
Bekannte Schaltverstärker verwenden die Pulsbreitenmodulation .Known switching amplifiers use pulse width modulation.
Beispiele solcher D- Verstärker sind z .B . in der Europäischen Patentanmeldung o 590 903 AI der Exar- Corporation und in der US-A 5, 247,581 der Exar-Cor- poration sowie den US-A 4,689,819 und US-A 4,592,087 der Industrial Research Products Inc . offenbart und ausführlich beschrieben .Examples of such D-amplifiers are, for example. in European Patent Application o 590 903 AI from Exar Corporation and in US Pat. Nos. 5, 247,581 to Exar Corporation and US Pat. Nos. 4,689,819 and 4,592,087 to Industrial Research Products Inc. disclosed and described in detail.
Solche D-Verstärker arbeiten im Prinzip wie folgt:Such D-amplifiers work in principle as follows:
Die im Ultraschallbereich liegende Rechteckimpulsfolge eines Oszillators wird einem Integrator zugeführt, dem außerdem die Ausgangsspannung eines Nieder¬ frequenzsignals zugeführt wird, das von einem Mikrofon über einen Verstärker¬ zug ankommt und als Vorspannung dient. Das Ausgangssignal des Integrators ist dann eine Dreiecks- Impulsfolge, deren Nulldurchgänge durch die dem
Integrαtor zugeführte, im Hörfrequenzbereich liegende Vorspannung variiert werden . D .h . , durch diese niederfrequente Vorspannung werden die Null¬ durchgänge des Dreieckssignals von einem zur Symmetrieachse symmetrischen Verlauf ohne Vorspannungssignal variabel zu unsymmetrischen Verhältnissen verschoben, wobei die Unsymmetrie bezüglich Vorzeichen und Größe eine kontinuierlich sich ändernde Funktion der Amplitude des niederfrequenten Eingangssignals ist.The rectangular pulse sequence of an oscillator, which is in the ultrasound range, is fed to an integrator, which is also fed the output voltage of a low-frequency signal, which arrives from a microphone via an amplifier train and serves as a bias voltage. The output signal of the integrator is then a triangular pulse train, the zero crossings through which Integrator supplied bias lying in the hearing frequency range can be varied. I.e. , this low-frequency bias voltage shifts the zero crossings of the triangular signal from a course symmetrical to the axis of symmetry without bias signal to asymmetrical conditions, the asymmetry in terms of sign and size being a continuously changing function of the amplitude of the low-frequency input signal.
Diese Nulldurchgänge werden dann zum Steuern des Zeitpunktes und der Pola¬ rität des Ausgangssignals einer polaritätsumkehrenden, symmetrischen CMOS- Schalt- Treiberstufe verwendet, die die Dauer der positiven und negativen Schaltimpulse entsprechend der zeitlichen Verschiebung zwischen den Null¬ durchgängen des Integrator-Ausgangssignals variiert, und damit ein impulsτ moduliertes Ausgangssignal an den Hörer mit einem Frequenzspektrum im Niederfrequenzbereich abgibt, das ein verstärktes Abbild des Ausgangssignals des Mikrofons darstellt.These zero crossings are then used to control the time and the polarity of the output signal of a polarity-reversing, symmetrical CMOS switching driver stage which varies the duration of the positive and negative switching pulses in accordance with the time shift between the zero crossings of the integrator output signal, and so that an impulsτ modulated output signal to the listener with a frequency spectrum in the low frequency range, which represents an amplified image of the output signal of the microphone.
Solche mit Impulsbreitenmodulation arbeitende D-Verstärker haben einen sehr guten Wirkungsgrad und weisen fast keine Kreuzmodulation auf .Such D-amplifiers working with pulse width modulation have a very good efficiency and have almost no cross modulation.
Ein Nachteil der D-Verstärker mit Impulsbreitenmodulation besteht darin, daß die Impulsbreite entweder kontinuierlich oder in ganz kleinen Schritten verän¬ dert werden sollte, wenn ein hohes Signal- zu Rausch-Verhältnis erreicht werden sol I .A disadvantage of the D-amplifier with pulse width modulation is that the pulse width should be changed either continuously or in very small steps if a high signal to noise ratio is to be achieved.
Die bekannten Klasse D-Ausgangsverstärker verwenden eine kontinuierliche Modulation, d .h . eine kontinuierliche Variation der Impulsbreite und benö¬ tigen daher ein kontinuierliches Ausgangssignal des Mikrofons als Eingangssignal , Wenn die dem Ausgangsverstärker vorangehende Signalverarbeitung zeitdiskret und / oder amplitudendiskret erfolgt, dann muß dieses digitale Signal zunächst,
z .B. in einen Hαltenetzwerk oder einen Digitαl/Anαlog-Wαndler umgewandelt werden . Dies stellt einen kaum vertretbaren zusätzlichen Aufwand dar .The known class D output amplifiers use continuous modulation, i.e. a continuous variation of the pulse width and therefore require a continuous output signal from the microphone as an input signal. If the signal processing preceding the output amplifier is time-discrete and / or amplitude-discrete, then this digital signal must first e.g. be converted into a network or a digit / analog converter. This represents an unreasonable additional effort.
Durch die Erfindung soll daher ein Hörhilfsgerät mit einem neuartigen wesent¬ lich einfacheren Ausgangsverstärker vorgeschlagen werden, bei dem ein relativ hohes Signal/Rauschverhältnis erreich-bar ist, bei extrem niedrigem Leistungs¬ bedarf und hoher Ausgangsleistung, mit geringsten Verzerrungen und jeglichem Fehlen von Kreuzmodulation sowie einer möglichen Ansteuerung des Ausgangs¬ signals mit einem digitalen oder einem analogen Eingangssignal . Der Ausgangs¬ verstärker kann dabei vollständig als digitale hochintegrierte CMOS-Schaltung aufgebaut werden .The invention is therefore intended to propose a hearing aid with a novel, considerably simpler output amplifier, in which a relatively high signal / noise ratio can be achieved, with extremely low power requirements and high output power, with minimal distortion and any lack of cross modulation and a possible control of the output signal with a digital or an analog input signal. The output amplifier can be constructed completely as a digitally highly integrated CMOS circuit.
Dies wird erfindungsgemäß mit den Merkmalen des Patentanspruches 1 erreicht.This is achieved according to the invention with the features of claim 1.
Weitere Merkmale der Erfindung sind den weitem Ansprüchen im einzelnen zu entnehmen.Further features of the invention can be found in the wide claims in detail.
Die Erfindung wird nunmehr anhand eines Ausführungsbeispieles in Verbindung mit den beigefügten Zeichnungen näher beschrieben .The invention will now be described in more detail using an exemplary embodiment in conjunction with the accompanying drawings.
In den Zeichnungen zeigt:In the drawings:
Fig . 1 ein Prinzipschaltbild eines Hörhilfsgerätes mit einem Aus¬ gangsverstärker gemäß der Erfindung;Fig. 1 shows a basic circuit diagram of a hearing aid with an output amplifier according to the invention;
Fig . 2 einen in dem Ausgangsverstärker des Hörhilfsgerätes ver¬ wendeten Signa Ikonverter undFig. 2 a Signa icon converter used in the output amplifier of the hearing aid and
Fig . 3 Impulsdiagramme zur Erläuterung der Arbeitsweise desFig. 3 pulse diagrams to explain the operation of the
Ausgangsverstärkers des Hörhilfsgerätes .
Fig. 1 zeigt beispielsweise ein Hörhilfsgerät mit einem neuartigen Ausgangsver¬ stärker, dessen Einsatz allerdings nicht auf die Verwendung in Hörhilfsgeräten beschränkt ist, sondern allgemein bei digitalen Verstärkern anwendbar ist, wo es auf ein hohes Verhältnis von Nutzsignal zu Störsignal ankommt.Output amplifier of the hearing aid. 1 shows, for example, a hearing aid device with a novel output amplifier, the use of which is not limited to the use in hearing aid devices, but is generally applicable to digital amplifiers where a high ratio of useful signal to interference signal is important.
Bei dem in Fig . 1 rein schematisch dargestel lten Hörhilfsgerät wird das akusti¬ sche Signal von einem Mikrofon 1 aufgenommen und in einem Tiefpaßfilter als Antialiasingfil ter auf einen bei Hörhilfsgeräten üblichen Frequenzbereich be¬ schränkt. Dieses niederfrequente Signal wird nun in einem Signalprozessor 3 einer Signal Verarbeitung unterzogen . Darunter ist z . B . zu verstehen, daß das analoge Eingangssignal entweder analog in der Weise weiterverarbeitet wird, daß die Verstärkerkenn linie des Signalprozessors an die für den jeweiligen Hörschaden oder Hörverlust seines Trägers bezüglich al ler erforderlichen Vari¬ ablen angepaßt wird .In the case of Fig. In a purely schematically illustrated hearing aid, the acoustic signal is picked up by a microphone 1 and limited in a low-pass filter as an anti-aliasing filter to a frequency range customary in hearing aids. This low-frequency signal is now subjected to signal processing in a signal processor 3. Among them is z. B. to understand that the analog input signal is either further processed analogously in such a way that the amplifier characteristic of the signal processor is adapted to the variables required for the respective hearing damage or hearing loss of its wearer with respect to all the variables.
Derartige, von der Frequenz abhängige beeinflußbare Variable sind z .B. die Verstärkung der einzelnen Stufen, der Begrenzungspegel , die Kompressions¬ schwel le, die automatische Verstärkungsregelung mit ihren Ansprech- und Abfallzeiten, eine Kombination von Kompression und Expansion oder überhaupt ein nichtlinearer Verlauf der Verstärkung einzelner Stufen oder insgesamt aller Stufen, sowie der Ausgangs-Schal Idruckpegel .Such variable, which are dependent on the frequency, are, for example. the amplification of the individual stages, the limit level, the compression threshold, the automatic amplification control with its response and decay times, a combination of compression and expansion or a non-linear course of the amplification of individual stages or all stages in total, as well as the output switching Pressure level.
Andererseits wird man wohl vorzugsweise eine digitale Signalverarbeitung vorsehen . In diesem Fal l müßte der Signalprozessor eingangsseitig einen Digi¬ tal -Ana log- Wandler enthalten, für den ein eigener Taktgenerator für die Takt¬ gabe erforderlich wäre . Dies ist allgemeiner Stand der Technik . Selbstverständ¬ lich sind dann al le oben genannten variablen Funktionen in digitaler Technik darstellbar.
Auf den Signa Iprozessor 3 folgt dann ein neuartiger Ausgangsverstärker. Dieser besteht im wesentlichen aus einem Signalkonverter 4, der im wesentlichen ein
ist. Dieser Signalkonverter enthält als erstes eine Subtrahier¬ stufe 5 mit zwei Eingängen, nämlich einem positiven Eingang und einem nega¬ tiven Eingang, wobei der positive Eingang am Ausgang des Signalprozessors 3 angeschlossen ist . Auf diese Subtrahierstufe 5 folgt ein Tiefpaßfilter 6. In der einfachsten Ausführung könnte das Tiefpaßfilter 6 ein Integrator sein . An diesem Integrator 6 ist eine Vergleichsstufe 7 mit Haltenetzwerk angeschlos¬ sen . Der Ausgang dieser Vergleichsstufe ist über eine RUckkopplungsverbindung mit dem negativen Eingang der Subtrahierstufe 5 verbunden . Außerdem ist ein Hochfrequenz-Taktgenerator 8 vorgesehen, der ein hochfrequentes Taktimpuls¬ signal mit einer Frequenz im Bereich von etwa 1 MHz an die VergleichsstufeOn the other hand, digital signal processing will probably be preferred. In this case, the signal processor on the input side would have to contain a digital-analog log converter, for which a separate clock generator would be required for the clock. This is the general state of the art. Of course, all of the above-mentioned variable functions can then be represented in digital technology. A new output amplifier then follows the Signal processor 3. This consists essentially of a signal converter 4, which is essentially a is. This signal converter first contains a subtractor stage 5 with two inputs, namely a positive input and a negative input, the positive input being connected to the output of the signal processor 3. This subtraction stage 5 is followed by a low-pass filter 6. In the simplest embodiment, the low-pass filter 6 could be an integrator. A comparison stage 7 with a holding network is connected to this integrator 6. The output of this comparison stage is connected via a feedback connection to the negative input of the subtraction stage 5. In addition, a high-frequency clock generator 8 is provided, which sends a high-frequency clock pulse signal with a frequency in the range of approximately 1 MHz to the comparison stage
7 abgibt . Der Ausgang des Signa Ikon verters 4 ist über eine Tiefpaßfun tion mit dem Hörer 10 verbunden .7 issues. The output of the Signa Ikon age 4 is connected to the receiver 10 via a low-pass function.
Ein für den Signa Iprozessor 3 erforderlicher Taktgenerator mit wesentlich niedrigerer Frequenz wird vorzugsweise durch den Hochfrequenz TaktgeneratorA clock generator with a significantly lower frequency required for the signal processor 3 is preferably provided by the high-frequency clock generator
8 synchronisiert. Dies kann beispielsweise in einfacher Weise durch Frequenz¬ teilung mit einem Faktor M erreicht werden . Eine typische Taktfrequenz für den Signa Iprozessor 3 könnte etwa 32 kHz sein .8 synchronized. This can be achieved, for example, in a simple manner by frequency division by a factor M. A typical clock frequency for the signal processor 3 could be about 32 kHz.
Die Wirkungsweise des Signalkonverters 4 soll anhand der Figuren 2 und 3 erläutert werden .The mode of operation of the signal converter 4 will be explained with reference to FIGS. 2 and 3.
Das hochfrequente Taktsignal 11 des Taktgenerators 8 wird, wie bereits erwähnt, der Vergleichsstufe 7 zugeleitet. Das digitale Eingangssignal 12 in Fig . 3 (eine extrem vereinfachte Darstellung) wird der Subtrahierstufe an ihrem positiven Eingang zugeführt . Das Ausgangssignal 14 des Signalkonverters 4 gelangt über eine Rückkopplungsverbindung an den negativen Eingang der Subtrahierstufe und wird dort vom Eingangssignal 12 subtrahiert.
Dαs dabei entstehende Ausgangssignal wird dem Integrator 6 (der hier das Tiefpaßfilter darstel lt) zugeführt und dort zum Ausgangssignal 13 integriert. Dieses Signal 13 wird in der Vergleichsstufe 7 mit Haltenetzwerk synchron mit den Flanken des hochfrequenten Taktsignals in das Ausgangssignal 14 umgewandelt, das nur zwei mögliche Werte aufweist, die hier der Einfah- heit halber als +1 und - 1 dargestellt sind .As already mentioned, the high-frequency clock signal 11 of the clock generator 8 is fed to the comparison stage 7. The digital input signal 12 in FIG. 3 (an extremely simplified representation) is fed to the subtraction stage at its positive input. The output signal 14 of the signal converter 4 reaches the negative input of the subtraction stage via a feedback connection and is subtracted there from the input signal 12. The resulting output signal is fed to the integrator 6 (which represents the low-pass filter here) and integrated there to form the output signal 13. This signal 13 is converted in the comparison stage 7 with holding network synchronously with the edges of the high-frequency clock signal into the output signal 14, which has only two possible values, which for the sake of simplicity are shown here as +1 and -1.
Das Eingangssignal 12 sol l zunächst den Wert -0,5 haben . Das integrierte Signal 13 steigt dann von - 1 ,5 auf Nul l an, was einen ersten Ausgangsimpuls¬ übergang von - 1 au +1 zur Folge hat. Das integrierte Signal fällt dann wie¬ der auf -1 ,5 ab, wonach das Aυsgangssignal 14 wieder den Wert -1 annimmt .The input signal 12 should initially have the value -0.5. The integrated signal 13 then rises from -1.5 to zero, which results in a first output pulse transition from -1 to +1. The integrated signal then drops again to -1, 5, after which the output signal 14 again assumes the value -1.
Der nachfolgende Anstieg des Eingangssignals 12 auf den Wert Nul l be¬ wirkt einen steileren Anstieg des integrierten Signals 13 auf den Wert 0,5. Für die Dauer des Eingangssignalpegels 0 erhält man dann über die Integra¬ tion die entsprechenden Signalwerte des Ausgangssignals 14 zwischen - 1 und + 1 , wobei jeweils die Werte - 1 dem unterenWert des integrierten Signals und die Werte +1 dem oberen Wert des integrierten Signals entsprechen .The subsequent rise in the input signal 12 to the value zero results in a steeper rise in the integrated signal 13 to the value 0.5. For the duration of the input signal level 0, the corresponding signal values of the output signal 14 between -1 and +1 are then obtained via the integration, the values -1 corresponding to the lower value of the integrated signal and the values +1 to the upper value of the integrated signal .
In gleicher Weise werden die weiteren Werte des Eingangssignals von 0,3, 0,6 und 1 ,0 über die Integration in entsprechende Impulse des Ausgangssignals 14 umgewandelt . D .h . in dem Ausgangssignal 14 ändert sich das Verhältnis von positiven Werten zu negativen Werten je Zeiteinheit in Abhängigkeit vom Eingangssignal 12.In the same way, the further values of the input signal of 0.3, 0.6 and 1.0 are converted into corresponding pulses of the output signal 14 via the integration. I.e. in the output signal 14 the ratio of positive values to negative values per time unit changes depending on the input signal 12.
Es ist ohne weiteres einleuchtend, daß dies eine sehr stark vereinfachte, stark gedehnte Darstel lung ist. Eine Takrfrequenz von etwa 1 MHz ließe sich zeich¬ nerisch nicht darstel len . Außerdem sind die Ampl itudenänderungen extrem vereinfacht als grobe Stufen dargestellt.
7493 PCI7EP95/02033It is obvious that this is a very simplified, greatly expanded presentation. A clock frequency of approximately 1 MHz could not be represented in the drawing. In addition, the amplitude changes are shown in extremely simplified form as rough steps. 7493 PCI7EP95 / 02033
- 7 -- 7 -
Bei der Umwandlung eines niederfrequenten Analogsignals in ein digitales Signal durch zeitdieskrete und/oder amplitudendiskrete Umwandlung wird das Analogsignal quantisiert. Die in Fig. 3 gezeigten Stufen des Eingangssig¬ nals 12 stehen also stellvertretend für entsprechende Amplitudenschritte eines qυantisierten Analogsignals .When converting a low-frequency analog signal into a digital signal by time-discrete and / or amplitude-discrete conversion, the analog signal is quantized. The stages of the input signal 12 shown in FIG. 3 therefore represent corresponding amplitude steps of a quantized analog signal.
Während man normalerweise bei einer Impulsbreitenmodulation üblicher Art mit Taktimpulsfrequen zen von z . B . 100 kHz auskommt, sind im vorliegenden Fall zur Erzielung eines großen Verhältnisses von Nutzsignal zu Störsignal wesentlich höhere Taktimpulsfrequenzen erforderlich, die beispielsweise im Bereich von 1 MHz liegen können .While normally with a pulse width modulation of the usual type with clock pulse frequencies of z. B. 100 kHz is sufficient, in the present case, to achieve a large ratio of useful signal to interference signal, significantly higher clock pulse frequencies are required, which can be, for example, in the range of 1 MHz.
Es ist offensichtlich, daß das Ausgangssignal 14 des Signalkonverters 4 neben dem erwünschten verstärkten niederfrequenten Anteil einen starken hochfre¬ quenten Signalanteil enthält, der natürlich ein unerwünschtes Störsignal darstellt, das z .B. durch ein passives Tiefpaßfilter entfernt werden muß.It is obvious that the output signal 14 of the signal converter 4 contains, in addition to the desired amplified low-frequency component, a strong high-frequency signal component which, of course, represents an undesired interference signal which, for example, must be removed by a passive low-pass filter.
Verwendet man diesen Ausgangsverstärker in einem Hörhilfsgerät, dann kann die Induktivität der Schwingspule des Hörers und die Tiefpaßeigenschaften des mechanischen und akustischen Systems des Hörhilfsgerätes und des menschlichen Ohres diese Tiefpaßfunktion vollkommen übernehmen, so daß ein gesondertes Tiefpaßfilter entbehrlich erscheint.If this output amplifier is used in a hearing aid, then the inductance of the voice coil of the listener and the low-pass properties of the mechanical and acoustic system of the hearing aid and the human ear can take over this low-pass function completely, so that a separate low-pass filter appears to be unnecessary.
Dieser neuartige, insbesondere für Hörhilfsgeräte geeignete Ausgangsverstär¬ ker hat eine Reihe von Vorteilen . Al le Impulsflanken sind mit einer bekannten Taktimpulsfrequenz synchronisiert, die zudem dazu verwendet werden kann, den für den vorgeschalteten Signa Iprozessor erforderlichen, bei wesentlich niedrigerer Taktfrequenz arbeitenden Taktimpulsgenerator zu synchronisieren .
Außerdem kann das Eingangssignal des Ausgangsverstärkers ein digitales Signal sein, und der Ausgangsverstärker kann als reine Digitalschaltung konzipiert werden . D.h . aber, daß die gesamte Schaltung als digitale Schaltung aufge¬ baut werden kann, wobei lediglich am Eingang des Signal rozessors 3 ein Analog/Digital-Wandler vorzusehen wäre . Daraus ergibt sich die weitere Möglichkeit, die gesamte Schaltung in C-MOS- Technik als hoch integrierte Schaltung aufzubauen .
This novel output amplifier, which is particularly suitable for hearing aids, has a number of advantages. All pulse edges are synchronized with a known clock pulse frequency, which can also be used to synchronize the clock pulse generator required for the upstream signal processor, which operates at a significantly lower clock frequency. In addition, the input signal of the output amplifier can be a digital signal and the output amplifier can be designed as a pure digital circuit. Ie. but that the entire circuit can be constructed as a digital circuit, an analog / digital converter only having to be provided at the input of the signal processor 3. This results in the further possibility of building up the entire circuit using C-MOS technology as a highly integrated circuit.
Claims
1 . Hörhilfsgerät mit einem Mikrofon (1 ), einem Übertragungsteil (2, 3) für die Signalverarbeitung, einem Ausgangsverstärker (4) und einem daran angeschlossenen Hörer (10) sowie mit einer Batterie für die Spannungsversorgung, dadurch gekennzeichnet, daß der Ausgangs¬ verstärker (4) aus einem Signalkonverter, der im wesentlichen als X-Δ -Konverter aufgebaut ist, einem daran angeschlossenen, ein hochfrequentes Taktsignal (1 1 ) erzeugenden Taktgenerator (8) und einer nach geschalteten Tiefpaßfilterfunktion (15) besteht, wobei das Eingangssignal des Signalkonverters (4) eine durch Signalverar- beitυng erzeugte Darstellung des niederfrequenten Eingangssignals des Hörhilfsgerätes ist, daß dieses Eingangssignal in demSignal- konverter in ein Signal umwandelbar ist, das nur zwei mögliche Signalwerte aufweist, und daß dieses Ausgangssignal (14) nach Durchlaufen der Tiefpaßfunktion als im wesentlichen verstärktes Abbild des niederfrequenten Eingangssignals erscheint .1 . Hearing aid with a microphone (1), a transmission part (2, 3) for signal processing, an output amplifier (4) and a receiver (10) connected to it, and with a battery for the voltage supply, characterized in that the output amplifier (4 ) consists of a signal converter, which is essentially constructed as an X-Δ converter, a clock generator (8) connected to it, which generates a high-frequency clock signal (1 1), and a downstream low-pass filter function (15), the input signal of the signal converter (4 ) A representation of the low-frequency input signal of the hearing aid device generated by signal processing is that this input signal can be converted in the signal converter into a signal which has only two possible signal values, and that this output signal (14) is substantially amplified after passing through the low-pass function Image of the low-frequency input signal appears.
2. Hörhilfsgerät nach Anspruch 1 , dadurch gekennzeichnet, daß der eingangsseitig an den Ubertragungsteil (2, 3) angeschlossene Signal¬ konverter (4) im wesentlichen aus einer Subtrahierstufe (5) mit einem positiven und einem negativen Eingang, einem Tiefpaßfilter (6) und einer durch einen Taktimpulsgenerator (8) mit hochfrequenten Takt¬ impulsen (1 1 ) gesteuerten Vergleichsschaltung (7) mit Haltenetzwerk besteht, wobei der positive Eingang der Subtrahierstufe (5) mit dem Übertragungsteil (2, 3) und der negative Eingang der Subtrahierstufe mit dem Ausgang der Vergleichsstufe (7) über eine Rückkopplungs- verbindung verbunden ist . 2. Hearing aid according to claim 1, characterized in that the signal converter (4) connected on the input side to the transmission part (2, 3) essentially consists of a subtraction stage (5) with a positive and a negative input, a low-pass filter (6) and there is a comparison circuit (7) with holding network which is controlled by a clock pulse generator (8) with high-frequency clock pulses (1 1), the positive input of the subtraction stage (5) with the transmission part (2, 3) and the negative input of the subtraction stage with the Output of the comparison stage (7) is connected via a feedback connection.
3. Hörhilfsgerät nach Anspruch 1 und 2, dadurch gekennzeichnet, daß das Eingangssignal (12) des Signalkonverters (4) ein Analogsignal ist .3. Hearing aid according to claim 1 and 2, characterized in that the input signal (12) of the signal converter (4) is an analog signal.
4. Hörhilfsgerät nach Anspruch 1 und 2, dadurch gekennzeichnet, daß das Eingangssignal (12) des Signalkonverters (4) ein zeitdiskretes Signal ist.4. Hearing aid according to claim 1 and 2, characterized in that the input signal (12) of the signal converter (4) is a discrete-time signal.
5. Hörhilfsgerät nach Anspruch 1 und 2, dadurch gekennzeichnet, daß das Eingangssignal des Signa Ikon verters in seiner Amplitude quan- tisiert ist.5. Hearing aid according to claim 1 and 2, characterized in that the input signal of the Signa Ikon is quantized in its amplitude.
ό. Hörhilfsgerät nach Anspruch 1 und 2, dadurch gekennzeichnet, daß das Eingangssignal des Signalkonverters eine aus mehreren Bits/Bytes bestehende digitale Darstel lung des Eingangssignals des Hörhilfsgerätes ist.ό. Hearing aid device according to claim 1 and 2, characterized in that the input signal of the signal converter is a digital representation of the input signal of the hearing aid device consisting of several bits / bytes.
7. Hörhilfsgerät nach Anspruch 1 bis 6, dadurch gekennzeichnet, daß die Taktfrequen z der durch den Taktgenerator (8) erzeugten Taktim¬ pulse im Bereich von 1MHz liegt .7. Hearing aid according to claim 1 to 6, characterized in that the clock frequencies z of the clock pulse generated by the clock generator (8) is in the range of 1 MHz.
8. Hörhilfsgerät nach Anspruch 1 bis ό, dadurch gekennzeichnet, daß das von einem Taktgenerator (9) zur Taktgabe an den Signa Iprozessor (3) abgegebene Taktsignal durch das hochfrequente Taktsignal (1 1 ) des Taktgenerators (8) synchronisierbar ist.8. Hearing aid according to claim 1 to ό, characterized in that the clock signal given by a clock generator (9) for clocking to the signal processor (3) can be synchronized by the high-frequency clock signal (1 1) of the clock generator (8).
9. Hörhilfsgerät nach Anspruch 1 bis 8, dadurch gekennzeichnet, daß die Tiefpaßfunktion durch die elektrischen, akustischen und mechani¬ schen Eigenschaften des Hörers (10) und gegebenenfal ls des menschli¬ chen Ohres gebildet ist. 9. Hearing aid according to claim 1 to 8, characterized in that the low-pass function is formed by the electrical, acoustic and mechanical properties of the earpiece (10) and, if applicable, the human ear.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE4441996A DE4441996A1 (en) | 1994-11-26 | 1994-11-26 | Hearing aid |
| DE4441996 | 1994-11-26 | ||
| PCT/EP1995/002033 WO1996017493A1 (en) | 1994-11-26 | 1995-05-29 | Hearing aid |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| EP0793897A1 true EP0793897A1 (en) | 1997-09-10 |
| EP0793897B1 EP0793897B1 (en) | 1998-05-13 |
Family
ID=6534142
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| EP95921771A Expired - Lifetime EP0793897B1 (en) | 1994-11-26 | 1995-05-29 | Hearing aid |
Country Status (9)
| Country | Link |
|---|---|
| US (1) | US5878146A (en) |
| EP (1) | EP0793897B1 (en) |
| JP (1) | JP3274469B2 (en) |
| AT (1) | ATE166199T1 (en) |
| AU (1) | AU691001B2 (en) |
| CA (1) | CA2204757C (en) |
| DE (2) | DE4441996A1 (en) |
| DK (1) | DK0793897T3 (en) |
| WO (1) | WO1996017493A1 (en) |
Cited By (1)
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|---|---|---|---|---|
| WO2019211187A1 (en) | 2018-04-30 | 2019-11-07 | Widex A/S | Method of operating a hearing aid system and a hearing aid system |
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| US5995036A (en) * | 1998-03-17 | 1999-11-30 | Sonic Innovations, Inc. | Passive switched capacitor delta analog-to-digital converter with programmable gain control |
| EP1133898B1 (en) * | 1999-01-25 | 2002-08-28 | Widex A/S | Hearing aid system and hearing aid for in-situ fitting |
| DE69906979T2 (en) * | 1999-02-05 | 2003-12-18 | Widex A/S, Vaerloese | HEARING AID WITH BEAM FORMING |
| US6445321B2 (en) | 1999-04-05 | 2002-09-03 | Sonic Innovations, Inc. | Hybrid low-pass sigma-delta modulator |
| US6163287A (en) | 1999-04-05 | 2000-12-19 | Sonic Innovations, Inc. | Hybrid low-pass sigma-delta modulator |
| US6408318B1 (en) | 1999-04-05 | 2002-06-18 | Xiaoling Fang | Multiple stage decimation filter |
| US6313773B1 (en) | 2000-01-26 | 2001-11-06 | Sonic Innovations, Inc. | Multiplierless interpolator for a delta-sigma digital to analog converter |
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| EP1251715B2 (en) | 2001-04-18 | 2010-12-01 | Sound Design Technologies Ltd. | Multi-channel hearing instrument with inter-channel communication |
| US7076073B2 (en) * | 2001-04-18 | 2006-07-11 | Gennum Corporation | Digital quasi-RMS detector |
| US20020191800A1 (en) * | 2001-04-19 | 2002-12-19 | Armstrong Stephen W. | In-situ transducer modeling in a digital hearing instrument |
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| US8098844B2 (en) * | 2002-02-05 | 2012-01-17 | Mh Acoustics, Llc | Dual-microphone spatial noise suppression |
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| DE102005006858A1 (en) | 2005-02-15 | 2006-09-07 | Siemens Audiologische Technik Gmbh | Hearing aid with an output amplifier comprising a sigma-delta modulator |
| DK1920633T3 (en) * | 2005-08-23 | 2011-10-03 | Widex As | Hearing aid with increased acoustic bandwidth |
| DK2417778T3 (en) | 2009-04-06 | 2015-07-27 | Widex As | Divided HEARING-AID WITH UNIT DATA CONNECTION |
| US8553897B2 (en) | 2009-06-09 | 2013-10-08 | Dean Robert Gary Anderson | Method and apparatus for directional acoustic fitting of hearing aids |
| US8879745B2 (en) * | 2009-07-23 | 2014-11-04 | Dean Robert Gary Anderson As Trustee Of The D/L Anderson Family Trust | Method of deriving individualized gain compensation curves for hearing aid fitting |
| US9101299B2 (en) * | 2009-07-23 | 2015-08-11 | Dean Robert Gary Anderson As Trustee Of The D/L Anderson Family Trust | Hearing aids configured for directional acoustic fitting |
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| WO2011110218A1 (en) | 2010-03-09 | 2011-09-15 | Widex A/S | Two part hearing aid with databus and method of communicating between the parts |
| US8942397B2 (en) * | 2011-11-16 | 2015-01-27 | Dean Robert Gary Anderson | Method and apparatus for adding audible noise with time varying volume to audio devices |
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-
1995
- 1995-05-29 AU AU26714/95A patent/AU691001B2/en not_active Expired
- 1995-05-29 CA CA002204757A patent/CA2204757C/en not_active Expired - Lifetime
- 1995-05-29 EP EP95921771A patent/EP0793897B1/en not_active Expired - Lifetime
- 1995-05-29 AT AT95921771T patent/ATE166199T1/en not_active IP Right Cessation
- 1995-05-29 US US08/836,260 patent/US5878146A/en not_active Expired - Lifetime
- 1995-05-29 DE DE59502189T patent/DE59502189D1/en not_active Expired - Lifetime
- 1995-05-29 DK DK95921771T patent/DK0793897T3/en active
- 1995-05-29 WO PCT/EP1995/002033 patent/WO1996017493A1/en active IP Right Grant
- 1995-05-29 JP JP50832196A patent/JP3274469B2/en not_active Expired - Lifetime
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| WO2019211187A1 (en) | 2018-04-30 | 2019-11-07 | Widex A/S | Method of operating a hearing aid system and a hearing aid system |
Also Published As
| Publication number | Publication date |
|---|---|
| AU2671495A (en) | 1996-06-19 |
| DK0793897T3 (en) | 1999-02-15 |
| CA2204757C (en) | 1999-08-03 |
| JP3274469B2 (en) | 2002-04-15 |
| CA2204757A1 (en) | 1996-06-06 |
| DE4441996A1 (en) | 1996-05-30 |
| DE59502189D1 (en) | 1998-06-18 |
| JPH10504155A (en) | 1998-04-14 |
| AU691001B2 (en) | 1998-05-07 |
| WO1996017493A1 (en) | 1996-06-06 |
| EP0793897B1 (en) | 1998-05-13 |
| ATE166199T1 (en) | 1998-05-15 |
| US5878146A (en) | 1999-03-02 |
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