EP1379102A2 - Sound localization in binaural hearing aids - Google Patents

Abstract

The method has the signal propagation time between an input transducer (2) for an input acoustic signal and an output transducer (4) converting an electrical signal into an output acoustic signal measured for the hearing aid (1) for a first ear, with transmission of a corresponding signal to the hearing aid (1') for the second ear, used for matching the signal propagation time between its corresponding input transducer (2') and output transducer (4'). An Independent claim for a binaural hearing aid system is also included.

Description

The invention relates to a hearing aid system and a method for setting a hearing aid system with at least one first and a second hearing aid, each at least an input transducer for receiving an acoustic Input signal and conversion into an electrical signal, a Signal processing unit for processing the electrical Signal and an output transducer for conversion of the electrical Include signals in an output signal and between them a signal path is provided for data transmission.

Directional listening is the ability of one Person to distinguish the direction in which a Sound source is located. If a sound source is not frontal or in front of the person, results by the finite speed of propagation of the sound inevitably a runtime difference between the two ears and thus a time difference, with which the ears one perceive sound wave coming from one direction. If a sound e.g. from the perspective of the peson comes from the right, reached this right ear for a fraction of a second rather than the left ear. This time difference is much shorter as the person concerned can consciously recognize. The effect occurs through an automatic integration process in the acoustic Nervous system.

In addition to the time difference is still a Difference in volume with which the ears make a sound perceive that comes from one side. A sound source on One side of the head conveys the ear on this page a slightly louder tone. Also this minimal difference in the volume is sufficient to allow the sound source from the View of the person can be located left or right.

Binaural hearing aid care is often a loss of direction hearing. This is mainly due to that depending on the hearing situation, that of the respective hearing aid is detected, the signal processing of the two Hearing aids may include different steps. Farther is in a hearing aid wearer usually the hearing loss Both ears pronounced different degrees. Corresponding are also the settings of the hearing aids to compensate set the hearing loss of each ear differently. Different settings of the signal processing However, both hearing aids usually have different signal propagation times within the hearing aids. It comes therefore to an unnatural shift of the for the Directional listening important phase of an acoustic input signal. As already mentioned, the term of a Sound signal between the two ears next to the difference in volume for directional listening of great importance. Already minor changes of this natural Runtime shift, such as different Signal propagation times within the hearing aids caused can therefore be a loss of directional hearing to lead.

To solve this problem is known to the two ears recorded acoustic signals in a common to process central signal processing device. So See US 5,479,522 next to two each worn on one ear Hearing aids an additional processor unit, the be executed for example as a breast appliance or wristwatch can. The acoustic signals recorded at both ears go through the same signal processing steps, so that get the phase relationship between the two signals remains.

From US 5,434,924 is known, the signal processing at binaural supply essentially only in one of the two To carry out hearing aids. These are the one ear transmit received signals to the hearing device of the other ear, processed there together and then fed to both ears (Master-slave solution).

The former solution has the disadvantage that another Assembly is necessary and the hearing aid wearer now three instead of two devices needed, which is a significant limitation wearing comfort, maintenance and handling. The second solution requires that the entire signal processing from a single signal processing unit to only a page must be made. While with the solution with There is enough room for a third device provide correspondingly powerful signal processing and to ensure their energy needs, is the place in one limited hearing aid on the ear. Therefore, a must Master-slave solution with two different trained Hearing aids inevitably have a lower computational capacity own as in the use of both hearing aids would be available.

Another approach to solving the above problem exists therein, the incoming sound signals to the hearing aids Both sides to the other device to transfer and to process both signals on each side. In this way go through the recorded on both ears acoustic Signals together the same steps of signal processing and therefore automatically experience the same signal delay. This approach is for example from the WO 97/14268 and WO 99/43185. The transfer of Microphone signals from both sides of a binaural hearing aid system to the other side and the simultaneous processing Both signals on both sides solves the problem a maturity difference, but is subject to the same restrictions like the master-slave approach.

Another major disadvantage of all mentioned solutions lies in the fact that they are all transmitting big Require datasets. This requires a considerable amount of time, Space and energy consumption. Especially with wireless data transfer, as he offered at the current state of the art is this represents a significant disadvantage.

From EP 0 941 014 A2 is a hearing aid system with a first and a second hearing aid known in which by actuation a control element on the first hearing aid control signals generated and transmitted to the second hearing aid. As a result, by the operation of the control element one of the hearing aids the simultaneous adjustment of both hearing aids causes.

From DE 100 48 354 A1 a method for operating a Hearing aid system known in the sound field characteristics of a be transmitted to the other hearing aid. It can are signal levels.

From DE 197 04 119 C1 a hearing aid is known in the a signal transmission from one to the other hearing aid over Light guide is made. In this case, control signals can be transmitted become.

Object of the present invention is in a hearing aid system for binaural care, natural directional hearing to support and the additional required for this Computing effort to keep low.

This object is achieved by methods with the features according to claims 1, 14 or 24.

Furthermore, the object is achieved by a hearing aid system with the Characteristics according to claims 32, 37, 39 or 43 solved.

In a known from the cited prior art Hearing aid system with two hearing aids will be the same Signal transit time in the signal paths of both hearing aids between each generated the microphone and the listener, without this signal delay to know explicitly. The disadvantage is the high computational complexity and the high data transfer rates required.

In contrast, sees an embodiment of the invention before, the signal propagation time of the electrical signal in the Signal path between the input transducer and the output transducer of the first hearing aid at least in a relevant Subarea, in which runtime differences are to be expected in principle are to detect and the signal transit time of the electric Signal between the input transducer and the output transducer of the second hearing aid to the determined signal propagation time to adapt to the first hearing aid.

Time differences between the two hearing aids one Hearing aid system arise in particular by different Settings of the hearing aids during operation. These different settings can be e.g. by a different hearing loss of the two ears of a Hearing aid wearer be conditional. In addition to the adaptation to the Hearing aid wearers can change the settings of a hearing aid also for adaptation to the respective environmental situation serve, in which the hearing aid is currently located. Because the last-mentioned settings in modern hearing aids can be done adaptively and automatically, the Run-time differences during the operation of the hearing aids vary.

In one embodiment of the invention, signal propagation times become of the first and second hearing aid. Preferably, suitable transit time measurements are carried out for this purpose. Advantageously, the determined signal propagation times comprise also the transit times of the input and output transducers, so that their delays are taken into account can. However, it can also only a portion of the Signal path between the input and the output transducer be measured.

Hearing aids usually have several hearing programs for adapting the signal processing to different ones Listening situations (e.g., "quiet environment", "background noise environment", "Drive in the car", "telephone conversation", etc.). Advantageously, the hearing aids are initially individually adapted to the hearing aid wearer and the signal delay for determines the various hearing programs. From a comparison the so determined for both hearing aids signal propagation times can for any program pairing (two hearing aids a hearing aid system can at different times at a time Listening programs operated) a signal delay to determine the signal transit time in the "faster" hearing aid, so the hearing aid with the shorter cycle time of an acoustic input signal of the input transducer to the output transducer, be extended must be the same with both hearing aids Signal delay. Is the information in a hearing aid about signal transit times for the individual hearing programs both hearing aids of a hearing aid system and the instantaneous Program pairing known and has this hearing aid about means for maturity change, so can thereby compensate for the difference in transit time. It must therefore only data for the identification of the current hearing program of a hearing aid transferred to the other hearing aid become. Alternatively, you can also use terms directly or transit time differences characterizing transfer data become.

Another embodiment of the invention provides that at a hearing aid a signal propagation time of an electrical Signal is detected automatically. Elaborate measurements the hearing aid can thereby be omitted. Furthermore is this embodiment is advantageous in a hearing aid device, which adapts adaptively to different listening situations, without a predefined division into hearing programs exhibit. The duration of an electrical signal between the input transducer and the output transducer then variable in a certain range and can be within this range of fluctuation assume almost any values. The signal delay is advantageous in such a hearing aid determined internally. For this purpose, for example the signal transit time through internal components, such as Signal processors or filters, under the current settings be known, so that to determine the total signal delay only the signal transit times of the individual Components must be added. On the other hand, the signal propagation time also be determined by means of a test signal, the advantageous fed to the input converter and before the output transducer is tapped.

In a further embodiment of the invention is for determining the signal delay of an acoustic input signal by the hearing aid or the signal delay of an electrical Signal through a portion of the hearing aid performed a correlation analysis. For example, can the correlation analysis between the electrical output signal of the microphone and the electrical input signal of the Handset to be performed. From the result of the correlation analysis goes the phase shift between the two Signals. From the phase shift can turn on the signal transit time will be closed.

In a further variant of the invention is provided that at two consecutive points in the signal path the hearing aid is formed in each case the envelope and from a comparison of the envelope the phase shift or the signal propagation time of the electrical signal between the both points is determined.

Data regarding the determined in a first hearing aid Signal propagation time will eventually come from the first hearing aid transferred to the second hearing aid. Likewise done also in the second hearing aid, the determination of the current Signal transit time and the transmission of related data from the second hearing aid to the first hearing aid.

For adaptation of different signal propagation times of two hearing aids a hearing aid system are different methods Applicable: On the one hand, it is possible with a digital one Hearing aid, the clock frequency of at least one component to change the hearing aid. So can the hearing aid clocked higher with the larger signal propagation time or the Hearing aid with the lower signal delay with reduced Clock frequency can be operated. On the other hand it is possible, the signal propagation time of the hearing aid with the lower Signal propagation time to increase by additional components. For example, in a digital hearing aid a shift register may be provided which receives the electrical signal in the signal path of the hearing aid to a certain Number of cycles delayed. Furthermore, filter media can also be used be used, which has a certain phase shift and cause delay. Preferably, as filter media Allpasses are used by means of which the phase shift can be adjusted and which does not affect show the frequency response.

The adaptation of the signal propagation times of two hearing aid devices Hearing aid system is carried out according to a variant of the invention at periodic intervals. This ensures that that the signal propagation times of the two hearing aids at most for a short period of time. The temporal Distances where an adjustment is made may be in the range minutes or hours.

Another variant of the invention provides that the determination and adaptation of the signal propagation times of two hearing aids of a hearing aid system following a parameter and / or functional change in at least one of the hearing aid devices he follows. This change can be made, for example, by manual Operation of at least one of the hearing aids by the user. For example, the user may switch cause the hearing aids to another hearing program. As a result, the signal processing in the hearing aids changes fundamentally are also changes in terms of the signal delay in the individual hearing aids to be expected. This will compensate for the changed signal propagation times carried out a new adjustment of the signal propagation times.

Just like with the manual operation of a control triggered parameter and / or function change takes place even with an automatic parameter and / or function change at least one hearing aid a compensation the signal transit times between the hearing aids. In order to can also be used in hearing aids, where an automatic Situation analysis and adaptation to the current situation Listening situation takes place, the signal transit time to the other Adjust the hearing aid. This is especially important because in such hearing aid systems due to the frequent in both hearing aids independently of each other Signal analysis different settings and functions to get voted. For example, with a hearing aid, in which feedback-induced oscillations are detected, an algorithm for feedback suppression active be set or a filter for feedback suppression without the other hearing aid is affected. So can runtime differences for the electrical signals in the individual hearing aids result.

Preferably, whenever at least one the hearing aids a parameter and / or functional change results in an adaptation of the signal propagation times of the two hearing aids carried out. This is especially advantageous when in both hearing aids automatically a steady and continuous adaptation to the respective environmental situation takes place, without this a fixed predetermined division in certain listening situations and a related one Assignment to predefined hearing programs is available.

In a hearing aid according to the prior art finds the Signal processing often in parallel in several parallel channels a signal processing unit instead. Includes Each channel usually typically has a specific frequency band of the signal to be processed. As a rule for the individual frequency bands a different signal processing takes place, the signal transit times between the individual bands vary. To even out this effect provides a variant of the invention, the signal transit times or the amplitude transfer behavior for the individual Determine frequency bands and between the hearing aids equalize.

In a hearing aid system according to the invention, directional hearing becomes thereby improving binaural hearing aid supply, that the signal delays attached to the two ears Hearing aids are aligned. The signal transit times however, are just one factor that affects directional hearing. In an advantageous embodiment of the hearing aid system According to the invention, an adaptation of the Amplitudenganges the two hearing aids. differences in the amplitudes of signals coming from different directions are mainly due to the shading effect of the head. The differences are in the amplitudes are very low and can not be consciously perceived become. Only by a very fine adjustment of hearing aids of a hearing aid system, these can be minimal Amplitude differences caused by different directions of incidence be maintained. The exact amount of these differences is rather secondary. It is important above all that an amplitude difference in a signal from a certain direction largely preserved remains, even if one or both hearing aids Change settings. If e.g. at a hearing aid the volume increases, so should the other Hearing aid to adjust the volume. However, since Often not both ears of a hearing aid wearer alike may be affected by hearing loss, the volume adjustment usually not with both hearing aids alike. Rather, the adaptation has below Considering the individual hearing curves, the two Ears of a hearing aid wearer were measured to take place. So it is crucial that a hearing aid wearer a signal that comes from a certain direction on the Ear with the shorter distance to the signal source always one a little higher volume is mediated.

In one embodiment of the invention is in a hearing aid system with two head-worn hearing aids one Amplification or gain change of an electrical signal determined in at least one of the hearing aids. The Gain change may e.g. by changing a parameter the signal processing of the hearing aid caused have been. Then data will be used to identify the current Reinforcement or for marking the gain change from the hearing aid to the other hearing aid of the hearing aid system. Also in this hearing aid then the gain is adjusted accordingly. This can mean that the gain changed by the same amount becomes. Preferably, the gain in the second Hearing aid, however, changed so that at one out of the 0-degree direction (directly from the front) incoming sound signal both ears through the supply of hearing aids again the same loudness impression arises. From the 0 degree direction deviating sound signals are then again with perceived different loudness impression, so that the Hearing aid wearer the direction from which the sound signal arrives, can perceive.

The value of a gain change in a hearing aid According to the invention, certain settings or functions be assigned permanently to the hearing aid. So, for example in a feedback suppression algorithm always provided a reduction of the gain by 10 dB be. Data identifying this gain change can then be activated as soon as the algorithm is active is transferred to the other hearing aid device of the hearing aid system be, so even with this a corresponding gain reduction is carried out. In many applications However, there is no fixed allocation between certain Functions of the hearing aid and related gain changes. The gain or gain change is then initially determined automatically in the hearing aid. For this purpose, signal amplitudes or signal levels of an electrical Signal on in the signal path of the hearing aid in a row recorded and evaluated. Also for this purpose, preferably a test signal in the signal path fed to the signal processing unit of the hearing aid at least partially. Preferably will also in the gain adjustment the gain in both Hearing aids and data relating to the each other hearing aid transmitted. To adapt the Gain in a hearing aid to a gain change in a second hearing aid device of a hearing aid system Filter media are preferably set. Preferably is also used in gain setting whenever at least one of the hearing aids has a parameter and / or function change, an adjustment of the gain the two hearing aids of a hearing aid system carried out. However, the gain adjustment can in periodic intervals. As well as the investigation and adjusting the signal propagation time can also be the determination and adjusting the gain or the amplitude transfer behavior in a hearing aid system with multi-channel hearing aids each referenced only to certain frequency bands be.

In an advantageous embodiment of the invention is in addition to the determination of signal propagation times in the hearing aids a hearing aid system and the transmission behavior measured by signal amplitudes. Again, a test signal fed at one point in the signal path and on subsequently read out again. Preferably This measurement also takes place for different signal frequencies. Then follows a parameter or function change in at least one of the hearing aids, so can the transmission behavior with respect to the signal amplitudes again measured and found differences in the transmission behavior become. Characteristic for the signal amplitudes Data is then transferred to the other hearing aid of the Hearing aid system transferred to adapt to the changed Transmission behavior.

The invention equally applies to behind the ear portable (BTE), in the ear portable (ido) or implantable Hearing aid systems application.

Figur 1 ein Hörgerätesystem mit zwei Hörhilfegeräten, zwischen denen ein Signalpfad vorgesehen ist und bei denen unterschiedliche Hörprogramme einstellbar sind,

Figur 2 ein Hörhilfegerät mit einer Signallaufzeit-Messeinrichtung und einem einstellbaren Verzögerungselement,

Figur 3 ein Hörhilfegerät mit einem Signallaufzeit- und Amplituden- Messelement und einstellbarer Taktfrequenz und

Figur 4 ein Hörhilfegerät, bei dem die Signalverarbeitung parallel in mehreren Frequenzkanälen erfolgt, mit einer Signalanalyse- und Steuereinheit.

Further details of the invention will be explained in more detail with reference to embodiments. Show it:

FIG. 1 shows a hearing aid system with two hearing aid devices, between which a signal path is provided and in which different hearing programs can be set,

FIG. 2 shows a hearing aid device with a signal transit time measuring device and an adjustable delay element,

3 shows a hearing aid with a signal delay and amplitude measuring element and adjustable clock frequency and

FIG. 4 shows a hearing aid device in which the signal processing takes place in parallel in a plurality of frequency channels, with a signal analysis and control unit.

FIG. 1 shows a schematic representation of a hearing aid system with two hearing aids 1 and 1 '. The hearing aids 1 and 1 'each include an acoustic-to-electrical input transducer (Microphone) 2 or 2 'for recording an acoustic Input signal and conversion into an electrical signal. The processing of the electrical signal to compensate the hearing loss of a hearing aid wearer takes place in the signal processing units 3 or 3 'instead. The processed signal finally becomes an electric-acoustic output transducer (Listener) 4 or 4 'converted back into a sound signal and the ears of a hearing aid wearer supplied.

To adapt to different listening situations, such as "Language in a quiet environment", "Speech with background noise", "Driving in the car," etc., include the hearing aids 1 and 1 'each have a control unit 5 or 5'. The control units 5 and 5 'are connected to memory units 6 and 6', respectively which different parameter sets for adapting the signal processing units 3 and 3 'to different listening situations are stored.

The attitude of the hearing aids 1 and 1 'to the respective Hearing situation is carried out by pressing a control element. 7 or 7 'on at least one of the hearing aid devices 1 or 1'.

According to the invention, in the hearing aids 1 and 1 ' Signal propagation times of the signal processing units 3 and 3 ' for the respective hearing programs and under consideration the respective settings of the hearing aids 1 and 1 'for Compensation of the individual hearing loss of a hearing aid wearer determined. This can be done, for example, by running time measurements during the adaptation of the hearing aids 1 and 1 'done. Are the signal propagation times for both hearing aids 1 and 1 'under the selected settings for the respective ones Hearing programs known, the hearing programs are the data for Identification of the signal propagation times assigned and also stored in the storage units 6 and 6 '. With this data It can be both the signal transit times as such also about the respective transit time differences between the individual Hearing programs or the hearing aids 1 and 1 'act. Now, if e.g. in the hearing aid 1 between two Hearing programs switched, so are from the storage unit 6 not only the parameters of the new hearing program are read, but also the newly assigned hearing program assigned Data for characterizing the signal propagation time. The latter will then via a transmitting and receiving unit 8 to the hearing aid 1 'transmitted. The hearing aid 1 'in turn receives by means of the transmitting and receiving unit 8 'of the data sent to the hearing aid 1 and leads them to the control unit 5 'to. This in turn compares the transferred ones Data with the information stored in the storage unit 6 ' regarding the duration of the currently selected hearing program. For example, by controlling a delay agent, in the embodiment as Allpassfilter 9 or 9 'is executed, then any runtime differences can be compensate. Advantageously, therefore, both hearing aids 1 and 1 ', the same signal propagation time between the input transducer 2 and the output transducer 4 and the input transducer 2 'and the output transducer 4'. So with the Hearing aid system 1, 1 'always allows directional hearing, regardless of the currently active program pairing of the hearing programs both hearing aids 1 and 1 '.

Another embodiment of the invention is shown in FIG 2. Da Here, too, both hearing aids of a hearing aid system that have the same equivalent circuit diagram is in Figure 2 only one of the two, in the embodiment, the hearing aid 11, shown. Also this includes as the hearing aid 1 and 1 'in the embodiment of Figure 1 is a microphone 12 for receiving an acoustic signal and conversion into a electrical signal, a signal processing unit 13 for frequency-dependent processing of the electrical signal and a handset 14 for converting the electrical signal in a acoustic output signal. The hearing aid device 11 further comprises an A / D converter 15 for converting the output of the Microphones in a digital signal and a D / A converter 16 for reconverting the digital signal into an analogue one Signal before the signal output via the handset 14.

In contrast to the embodiment of FIG 1 is done in the hearing aid device 11 according to FIG. 2, a signal analysis of the digital electrical input signal in an analysis and Control unit 17. This is also a memory unit 18th connected, in the different, the signal processing relevant storage records are storable. Besides the possibility the control of signal processing in the hearing aid 11 by a complete parameter set, which is in the memory unit 18 is stored in the hearing aid 11 provided, even only individual settings and parameters for Adjustment of the signal processing to the respective listening situation adaptively to change. Also may be specific Functions or algorithms switched on or off become. Thus, in the hearing aid when recognized language a speech enhancement algorithm can be set or it can detect interfering noise an algorithm for noise reduction be switched active. It is thus one Variety of different settings and functions possible, Mostly affect the signal transit time of a Have signal through the hearing aid 11. Therefore, at the Hearing aid 11, the signal propagation time under consideration the current settings and functions automatically. For this purpose, the hearing aid device 11 has a transit time determination unit 19 on. This includes a signal generator for Generating and injecting a synthetic signal into the Signal path. The injected signal passes through the signal processing unit 13 and will be over the listener before the issue 14 tapped and the runtime determination unit 19 supplied. Preferably, the generated signal is in one of the hearing aid wearer acoustically imperceptible frequency range. By the runtime determination unit 19 can now the Signal transit time measured by the signal processing unit 13 and transmitted to the analysis and control unit 17. The transit time measurement is advantageously always carried out when the hearing aid 11 a parameter or Function change has resulted. The determined, the signal transit time Finally, the data in question will be Transmitting and receiving unit 20 to the second hearing aid (not shown) of the hearing aid system transmitted. As well The hearing aid device 11 also receives by means of the transmission and Receiving unit 20, the current signal propagation through the signal processing unit of the second hearing aid. In the analysis and control unit 17 is thus the information regarding the signal propagation times of both hearing aids of the Hearing aid system. For the hearing aid with the shorter determined signal delay, in the embodiment, the hearing aid 11, below is a signal delay around the Difference of the signal propagation times determined in both hearing aid devices carried out. For this purpose, the hearing aid device 11 includes a delay unit formed as a shift register 21. In this case, the number of delay clocks is determined by the analysis and control unit 17 adjustable. It will be advantageous also achieved in this embodiment, that for the passage an acoustic input signal in parallel by two hearing aids a hearing aid system the same signal transit time is needed.

A further embodiment of the invention is shown in FIG. 3 shown. In this case, a hearing aid 22 shows an embodiment 2 very similar structure. In difference to the hearing aid device 11 according to Figure 2, the Hearing aid 22, however, a clock generator 23 with adjustable Clock frequency on. By means of the adjustable clock generator 23, the system clock of the hearing aid 22 is adjustable. Depending on the system clock, the signal propagation time is one Signal by the hearing aid 22 changeable. Is in analogous to the hearing aid device described in FIG found that the signal propagation time compared to a second Hearing aid of the hearing aid system is longer, then becomes Compensation of the transit time difference increases the clock frequency so much until the runtime difference is balanced. Corresponding is determined at one for the hearing aid 22 shorter signal propagation time the clock frequency of the hearing aid 22 reduced so that the signal propagation times adjusted are.

In a preferred embodiment of the invention takes place in addition to the compensation of signal propagation times with changed settings and functions at least one hearing aid also an amplitude compensation. For this, e.g. analogous to Compensation of signal propagation times in the hearing aids 1 and 1 'are determined according to Figure 1 gain values and related thereto Data is stored in the storage units 6 and 6 ' become. At a gain change in one of both hearing aids due to a parameter and / or functional change (e.g., changing the hearing program) then becomes the Amplification in the other hearing aid adapted accordingly.

Also in the example illustrated in Figures 2 and 3 Hearing aids can be made an amplitude compensation. This is advantageous via the measuring device 19 a Test signal fed into the signal path and at a later Position in the signal path, preferably after the signal processing unit 13, again tapped. In addition to the signal transit time becomes so advantageous also the signal transmission behavior measured in terms of signal amplitudes. Preferably takes place the measurement at different frequencies. So can in each case a specific gain value for different frequencies be determined. Data regarding the thus determined Gain values will then be on top of each other Transfer hearing aid device of the hearing aid system. following there is an adjustment of the signal amplitudes, wherein at least one of the hearing aids changed the gain or Filter media can be adjusted. Advantageously, the adjustment follows the signal amplitudes taking into account the both ears measured audiograms. Data regarding this Audiograms may also be stored in the storage units 18 be. The loudness compensation then takes place in relation to the audiograms, which achieves that, for example one by a parameter change to a hearing aid caused minor loudness change one subjectively same loudness change for the hearing aid wearer on the other hearing aid causes. This will be minor Loudness differences in the two ears of a hearing aid wearer regardless of the current hearing aid settings always perceived the same.

A further embodiment of the invention is shown in FIG. 4 shown. Also, Figure 4 shows only a hearing aid 24 of a Hearing aid system with two identically designed hearing aids. The hearing aid device 24 includes two microphones 25 and 26, the output signals of a signal preprocessing unit 27 are supplied. In the signal preprocessing unit 27 An A / D conversion and an electrical connection takes place the microphone signals for generating a directional microphone characteristic. A filter bank 28 serves to split the electrical Signals in frequency bands. In signal processing units 29A, 29B, 29C and 29D is then a frequency band specific Signal processing of the electrical signals in the individual frequency bands. Finally, the output signals of the signal processing units 29A to 29D and post-processed in a signal post-processing unit 30. The signal post-processing can, for example, a Final amplification and D / A conversion include. Finally will the analog electrical output signal through a handset 31st converted back to an acoustic output signal. The single ones Signal processing blocks of the hearing aid, so the signal pre-processing unit 27, the filter bank 28, the Signal processing units 29A to 29D in the individual channels and the signal postprocessing unit 30, are in Embodiment summarized as a signal processing unit Designated 29.

Also in the hearing aid 24 in this embodiment are different hearing programs for adjusting the signal processing in the hearing aid to different listening situations intended. Corresponding parameter sets are in one Memory unit 32 deposited. To recognize the momentary Hearing situation, the hearing aid device 24 has a signal analysis and control unit 33, in which the electrical input signal before splitting into different frequency bands and the electrical output signal after passage the signal processing units 29A to 29D. through the signal analysis and control unit 33 may, for example feedback oscillations in the electrical Input signal to be detected. As a countermeasure against detected feedback oscillations can then in a frequency band in which the oscillation frequency lies, For example, the gain can be reduced. Data regarding this gain change in the channel in question are then detected by the signal analysis and control unit 33 and by means of a transmitting and receiving unit 34 on the second hearing aid (not shown) transferred. This receives the transmitted data and in turn lowers the Gain in the corresponding channel by means of one of Signal analysis and control unit of the hearing aid 24 corresponding Signal analysis and control unit. Likewise also data regarding a gain change in the second Hearing aid device of the hearing aid system on the hearing aid 24 transmitted by the signal analysis and Control unit 33 to components (for example, the signal processing units 29A to 29D in each channel) acting and the gain in the hearing aid 24 adapts accordingly.

The gain change can in both hearing aids to the same amount. Preferably, however, it is done taking into account the individual hearing loss of the Hearing aid carrier and the signal transmission characteristics of the Hearing aids. The hearing aid wearer then subjectively takes the same gain reduction on both hearing aids true. Natural loudness differences in the acoustic Input signals thus remain for the hearing device wearer largely preserved.

Often parameter or functional changes lead to hearing aids not too pre-determined due to the current hearing situation Gain changes. This is for example Hearing aids of the case, where not complete parameter sets to adapt to different listening situations are given, but where an adaptive and continuous Adaptation of individual parameters takes place. A gain change is then advantageous by a hearing aid internal measurement determined. Thus, in the hearing aid according to Figure 4 shows the gain change from measurements of the gain detected before and after a parameter change become. For this purpose, the electrical input signal as well the electrical output signal in the signal analysis and Control unit 33 evaluated. In the embodiment according to FIG. 4 is an evaluation of the total input signal. or output signal as well as the electrical input and Output signals of the signal processing units 29A to 29D the individual channels possible, depending on whether a parameter change the entire frequency range or only signal frequencies within a frequency band.

Analogous to the adjustment of the gain can in a hearing aid system with two hearing aids with a schematic Block diagram according to the exemplary hearing aid 24, as shown in Figure 4, the signal amplitudes or the signal propagation times of the two hearing aids are adapted to each other so that natural directional listening is also at worn hearing aids. Here are for the amplitude or delay compensation over the gain compensation only other signal analysis methods in the Signal analysis and control unit 33 provide. So go that Amplitude compensation, for example, amplitude or level measurements or the runtime compensation, phase or signal delay measurements on the overall signal or in the individual channels the hearing aid 24 ahead. The compensation then takes place preferably by adjustable filter means within the Signal processing unit 29, through the signal analysis and control unit 33 are set.

In a preferred variant, the runtime measurement is a Correlation analysis performed. For this, the signal analysis and control unit 33 electrical signals from one behind the other Points in the signal path between the microphones 25 and 26 and the handset 31 supplied. By means of the correlation analysis can then phase shift and thus the signal transit time can be determined easily.

In a further preferred variant, in the signal analysis and control unit first the envelopes of the supplied Signals detected. Also from the comparison of the envelopes in the signal analysis and evaluation 33 easy on the phase shift of the relevant signals and thus on the signal transit time between the considered Points in the signal path of the hearing aid 24 inferred become.

The measurements are made in each case shortly before and shortly after parameter or function changes in the hearing aid 24, to the resulting gain and / or Amplitude and / or signal delay changes in the hearing aid 24, related data to the second To transfer hearing aid of the hearing aid system, there to receive, evaluate and finally compensate for the changes.

In summary, it is stated:

For the binaural supply of a hearing aid wearer with two Ear hearing aids should listen to direction be improved. For this purpose, the invention proposes, respectively Signal propagation times and / or signal amplitudes and / or amplifications an electrical signal in a signal path between an input transducer and an output transducer of a Hearing aid to measure and data on the measured Signal propagation times and / or signal amplitudes and / or amplifications to transfer to the other hearing aid. This allows the signal propagation times and signal amplitudes the electrical signals through the two hearing aids to each other be adjusted. This is by the hearing aids causes no phase or amplitude distortion and the natural phase shift as well as the natural amplitude difference one from a certain direction Sound signal is retained. Thus, the remains Direction information for the hearing aid wearer received.

Claims (44)

A method for setting a hearing aid system having at least one first (1, 11, 22, 24) and a second (1 ') hearing aid, each having at least one input transducer (2, 2', 12, 25, 26) for receiving an acoustic input signal and Conversion into an electrical signal, a signal processing unit (3, 3 ', 13, 29) for processing the electrical signal and an output transducer (4, 4', 14, 31) for converting the electrical signal into an output signal and between which a signal path (10) is provided for data transmission, characterized in that a signal propagation time of the electrical signal in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24) is determined and a signal via the signal path (10) to the second hearing aid (1 ') is transmitted to adjust the signal propagation time of the electrical signal in the signal path between the input transducer (2') and the output transducer (4 ') of the second hearing aid device (1') to the determined signal propagation time of the electrical signal in the first hearing aid device (1, 11, 22, 24). A method according to claim 1, characterized in that for the passage of the electrical signal through at least a portion of the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid device (1, 11, 22, 24) required signal transit time is determined. A method according to claim 1 or 2, characterized in that the signal propagation time of the electrical signal in the first hearing aid (1, 11, 22, 24) automatically determined and a signal to the second hearing aid (1 ') is transmitted. Method according to one of claims 1 to 3, characterized in that for determining the signal propagation time, the envelope of the electrical signal is determined and the phase shift of the envelope is determined. Method according to one of claims 1 to 3, characterized in that for determining the signal propagation time, a correlation analysis is performed. Method according to one of claims 1 to 5, characterized in that for determining the signal propagation time, a test signal is generated which the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24) at least partially passes. Method according to one of claims 1 to 6, characterized in that the signal propagation time in the first (1, 11, 22, 24) and the second (1 ') hearing aid is determined and in each case a signal is transmitted to the other hearing aid. A method according to claim 7, characterized in that in the hearing aid device (1, 1 ', 11, 22, 24) with the shorter detected signal propagation time, a signal delay is performed. Method according to one of claims 1 to 8, characterized in that in at least one of the hearing aid devices (1, 1 ', 11, 22, 24), the signal processing unit (3, 13, 29) is at least partially executed in digital circuit technology and to adapt the Signal propagation time, the clock frequency of at least one digital component (13, 15, 16) is adjusted. Method according to one of claims 1 to 9, characterized in that for adjusting the signal propagation time filter means (9, 9 ') are set. Method according to one of claims 1 to 10, characterized in that the determination and adaptation of the signal propagation time occur at periodic intervals. Method according to one of claims 1 to 10, characterized in that the determination and adaptation of the signal propagation time following a parameter and / or functional change in at least one of the hearing aid devices (1, 1 ', 11, 22, 24) take place. Method according to one of claims 1 to 12, characterized in that the signal processing in the first (1, 11, 22, 24) and the second (1 ') hearing aid in a plurality of parallel frequency channels of the respective signal processing unit (3, 13, 29) and the detection and adaptation of the signal propagation time in each case take place in at least one frequency channel. A method for setting a hearing aid system having at least one first (1, 11, 22, 24) and a second (1 ') hearing aid, each having at least one input transducer (2, 2', 12, 25, 26) for receiving an acoustic input signal and Conversion into an electrical signal, a signal processing unit (3, 3 ', 13, 29) for processing the electrical signal and an output transducer (4, 4', 14, 31) for converting the electrical signal into an output signal and between which a signal path (10) is provided for data transmission, characterized in that a gain or gain change of the electrical signal in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid device (1, 11, 22, 24) is detected and a signal via the signal path (10) to the second hearing aid (1 ') is transmitted to adjust the gain of the electrical signal in the signal path between the input transducer (2 ') and the output transducer (4') of the second hearing aid (1 ') to the determined gain of the electrical signal in the first hearing aid (1, 11, 22, 24). A method according to claim 14, characterized in that the gain or gain change of the electrical signal for a portion of the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11 , 22, 24) is determined. The method of claim 14 or 15, characterized in that the gain or gain change of the electrical signal in the first hearing aid (1, 11, 22, 24) is automatically determined and a signal to the second hearing aid (1 ') is transmitted. Method according to one of claims 14 to 16, characterized in that for determining the gain or gain change, a test signal is generated, which determines the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid device (1, 11, 22, 24) at least partially passes. Method according to one of Claims 14 to 17, characterized in that signal amplitudes and / or signal levels of the electrical signal are determined in order to determine the gain or gain change. Method according to one of claims 14 to 18, characterized in that the gain or gain change in the first (1, 11, 22, 24) and the second (1 ') hearing aid device is determined and in each case a signal is transmitted to the other hearing aid. Method according to one of Claims 14 to 19, characterized in that filter means (9, 9 ') are adjusted to adapt the gain. Method according to one of claims 14 to 20, characterized in that the determination and adaptation of the gain or gain change take place at periodic intervals. Method according to one of claims 14 to 21, characterized in that the determination and adjustment of the gain following a parameter and / or functional change in at least one of the hearing aid devices (1, 1 ', 11, 22, 24) take place. Method according to one of claims 14 to 22, characterized in that the signal processing in the first (1, 11, 22, 24) and the second (1 ') hearing aid in several parallel frequency channels of the respective signal processing unit (3, 13, 29) and the determination and adaptation of the gain in each case take place in at least one frequency channel. A method for setting a hearing aid system having at least one first (1, 11, 22, 24) and a second (1 ') hearing aid, each having at least one input transducer (2, 2', 12, 25, 26) for receiving an acoustic input signal and Conversion into an electrical signal, a signal processing unit (3, 3 ', 13, 29) for processing the electrical signal and an output transducer (4, 4', 14, 31) for converting the electrical signal into an output signal and between which a signal path (10) is provided for data transmission, characterized in that a signal amplitude of the electrical signal in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24) is determined and a signal via the signal path (10) to the second hearing aid (1 ') is transmitted to adjust the signal amplitude of the electrical signal in the signal path between the input transducer (2 ') and the output transducer (4') of the second hearing aid (1 ') to the determined signal amplitude of the electrical signal in the first hearing aid (1, 11, 22, 24). A method according to claim 24, characterized in that the signal amplitude of the electrical signal in the first hearing aid (1, 11, 22, 24) is automatically determined and a signal to the second hearing aid (1 ') is transmitted. A method according to claim 24 or 25, characterized in that for determining the signal amplitude, a test signal is generated, the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid device (1 , 11, 22, 24) at least partially. Method according to one of claims 24 to 26, characterized in that the signal amplitude in the first (1, 11, 22, 24) and the second (1 ') hearing aid is determined and in each case a signal is transmitted to the other hearing aid. Method according to one of Claims 24 to 27, characterized in that filter means (9, 9 ') are set to adapt the signal amplitude. Method according to one of claims 24 to 28, characterized in that the determination and adjustment of the signal amplitude take place at periodic intervals. Method according to one of claims 24 to 29, characterized in that the determination and adaptation of the signal amplitude following a parameter and / or function change in at least one of the hearing aid devices (1, 1 ', 11, 22, 24) take place. Method according to one of claims 24 to 30, characterized in that the signal processing in the first (1, 11, 22, 24) and the second (1 ') hearing aid device takes place in several parallel frequency channels of the respective signal processing unit (3, 13, 29) and the determination and adaptation of the signal amplitudes in each case take place in at least one frequency channel. Hearing aid system comprising at least a first (1, 11, 22, 24) and a second (1 ') hearing aid, each having at least one input transducer (2, 2', 12, 25, 26) for receiving an acoustic input signal and conversion into an electrical Signal, a signal processing unit (3, 3 ', 13, 29) for processing the electrical signal and an output transducer (4, 4', 14, 31) for converting the electrical signal into an output signal and between which a signal path (10) for Data transmission is provided, characterized in that the first hearing aid (1, 11, 22, 24) comprises means for measuring and means for transmitting data relating to a signal propagation time of an electrical signal in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24) and the second hearing aid (1 ') means for receiving the transmitted data and means for adjusting a signal delay in the signal path z between the input transducer (2 ') and the output transducer (4') of the second hearing aid device (1 ') to the signal delay of the electrical signal in the first hearing aid device (1, 11, 22, 24). Hearing aid system according to claim 32, characterized in that by the means for measuring the signal propagation time of the electrical signal, a correlation analysis is feasible. Hearing aid system according to claim 32 or 33, characterized in that at least one of the hearing aid devices (1, 1 ', 11, 22, 24) comprises means for signal delay. Hearing aid system according to one of claims 32 to 34, characterized in that the signal processing units (3, 3 ', 13, 29) of the first (1, 1', 11, 22, 24) and the second (1 ') hearing aid in digital circuit technology are executed and clocked and at least one of the hearing aid devices (22) comprises means for clock change. Hearing aid system according to one of claims 32 to 35, characterized in that the signal processing in the first (1, 11, 22, 24) and the second (1 ') hearing aid in a plurality of parallel frequency channels of the respective signal processing unit (3, 3', 13, 29) and at least the first hearing aid device (1, 11, 22, 24) comprises means for determining the signal propagation time and at least the second hearing aid device (1 ') comprises means for adapting the signal propagation time in at least one frequency channel. Hearing aid system comprising at least a first (1, 11, 22, 24) and a second (1 ') hearing aid, each having at least one input transducer (2, 2', 12, 25, 26) for receiving an acoustic input signal and conversion into an electrical Signal, a signal processing unit (3, 3 ', 13, 29) for processing the electrical signal and an output transducer (4, 4', 14, 31) for converting the electrical signal into an output signal and between which a signal path (10) for Data transmission is provided, characterized in that the first hearing aid (1, 11, 22, 24) comprises means for measuring and means for transmitting data relating to a gain or gain change of an electrical signal in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24) and the second hearing aid (1 ') means for receiving the transmitted data and means for adjusting an amplifier kung in the signal path between the input transducer (2 ') and the output transducer (4') of the second hearing aid (1 to the gain or gain change of the electrical signal in the first hearing aid (1, 11, 22, 24). Hearing aid system according to one of claims 32 to 35, characterized in that the signal processing in the first (1, 11, 22, 24) and the second (1 ') hearing aid in a plurality of parallel frequency channels of the respective signal processing unit (3, 3', 13, 29) and at least the first hearing aid device (1, 11, 22, 24) comprises means for determining the gain or gain change and at least the second hearing aid device (1 ') comprises means for adjusting the gain in at least one frequency channel. Hearing aid system comprising at least a first (1, 11, 22, 24) and a second (1 ') hearing aid, each having at least one input transducer (2, 2', 12, 25, 26) for receiving an acoustic input signal and conversion into an electrical Signal, a signal processing unit (3, 3 ', 13, 29) for processing the electrical signal and an output transducer (4, 4', 14, 31) for converting the electrical signal into an output signal and between which a signal path (10) for Data transmission is provided, characterized in that the first hearing aid (1, 11, 22, 24) comprises means for measuring and means for transmitting data relating to a signal amplitude of an electrical signal in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24) and the second hearing aid (1 ') means for receiving the transmitted data and means for adjusting a signal amplitude in the signal path between the input transducer (2 ') and the output transducer (4') of the second hearing aid device (1 ') to the signal amplitude of the electrical signal in the first hearing aid device (1, 11, 22, 24). Hearing aid system according to one of claims 32 to 35, characterized in that the signal processing in the first (1, 11, 22, 24) and the second (1 ') hearing aid in a plurality of parallel frequency channels of the respective signal processing unit (3, 3', 13, 29) and at least the first hearing aid device (1, 11, 22, 24) comprises means for determining the signal amplitude and at least the second hearing aid device (1 ') comprises means for adapting the signal amplitude in at least one frequency channel. Hearing aid system according to one of claims 32 to 40, characterized in that the first hearing aid device (1, 11, 22, 24) at least one transmitting unit (8, 8 ', 20, 34) and the second hearing aid device (1') at least one receiving unit ( 8 ') for wireless signal transmission between the first (1, 11, 22, 24) hearing aid device and the second (1') hearing aid device. Hearing aid system according to one of claims 32 to 41,
characterized in that at least the first (1, 11, 22, 24) hearing aid comprises means for generating a test signal. Hearing aid system comprising at least a first (1, 11, 22, 24) and a second (1 ') hearing aid, each having at least one input transducer (2, 2', 12, 25, 26) for receiving an acoustic input signal and conversion into an electrical Signal, a signal processing unit (3, 3 ', 13, 29) for processing the electrical signal and an output transducer (4, 4', 14, 31) for converting the electrical signal into an output signal and between which a signal path (10) for Data transmission is provided, characterized in that the first hearing aid device (1, 11, 22, 24) comprises means for storing and means for transmitting data relating to a signal propagation time of an electrical signal in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24) and the second hearing aid (1 ') means for receiving the transmitted data and means for adjusting a signal delay in the signal path d between the input transducer (2 ') and the output transducer (4') of the second hearing aid device (1 ') to the signal delay of the electrical signal in the first hearing aid device (1, 11, 22, 24). Hearing aid system according to claim 43, characterized in that in the first hearing aid device (1, 11, 22, 24) a plurality of parameter sets for adapting the signal processing in the first hearing aid (1, 11, 22, 24) can be stored and adjusted to different listening situations and at least a parameter set data with respect to the signal delay of an electrical signal in the signal path between the input transducer (2, 12, 25, 26) and the output transducer (4, 14, 31) of the first hearing aid (1, 11, 22, 24) are assigned.

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