Method for operating a hearing device and hearing device

Abstract

The invention relates to a method (26) for operating a hearing aid (2) comprising a microphone (6) and a receiver (12) which are connected by means of a signal processing unit (10). An input signal (30) is provided, and a signal component (36) of the input signal (30) having a specific frequency (40) is selected. Another signal (44) with a further specific frequency (46) is provided, and an output signal (50) is generated based on the signal component (36) and the further signal (44). The output signal (50) is output via the receiver (12), thus producing a sound.The further signal (44) is configured such that first time intervals (54) and second time intervals (56) result, wherein during the first time intervals (54) hair cells located in a region (22) of a user's basilar membrane (20) associated with a specific frequency (40) are stimulated due to interference, and wherein during the second time intervals (56) the hair cells are not stimulated. The invention further relates to a hearing aid (2).

Description

[0001] The invention relates to a method for operating a hearing aid and to a hearing aid itself. The hearing aid comprises a microphone and a receiver, which are connected by means of a signal processing unit.

[0002] People with hearing loss typically use a hearing aid. This device usually uses a microphone, i.e., an electromechanical transducer, to convert ambient sound into an electrical (audio / sound) signal, thus providing an input signal. This input signal is processed by an amplifier circuit and then delivered to the person's ear canal via another electromechanical transducer, in the form of a receiver. Often, the captured input signal is further processed according to the degree of hearing loss, typically using a signal processing unit, which may include the amplifier circuit.

[0003] Typically, an audiologist first determines which frequencies of the unaltered input signal the user can only perceive to a reduced degree. During normal use of the hearing aid, the signal processing unit then increases the amplitude of these frequencies, thus amplifying these components of the input signal. However, it is also possible that certain frequencies, usually relatively high frequencies, cannot be perceived by a user at all. In this case, the signal processing unit shifts the corresponding components of the input signal to lower frequencies, a process also known as compression.

[0004] All of these methods only alleviate or modify symptoms. However, they do not address the underlying physiological changes in the user that lead to the reduction in hearing ability. Therefore, the effectiveness of these methods is inherently limited.

[0005] The invention is based on the objective of providing a particularly suitable method for operating a hearing aid and a particularly suitable hearing aid, wherein in particular performance is increased.

[0006] With regard to the method, this problem is solved by the features of claim 1, and with regard to the hearing aid by the features of claim 9. Advantageous further developments and embodiments are the subject of the dependent claims.

[0007] The process is used to operate a hearing aid. For example, the hearing aid is a headphone or includes a headphone, and the hearing aid is, for example, a headset. However, the hearing aid is most commonly referred to as a hearing aid device. The hearing aid device serves to support a person suffering from a reduction in hearing ability. In other words, the hearing aid device is a medical device by means of which, for example, partial hearing loss is compensated. The hearing aid device is, for example, a receiver-in-the-canal (RIC) hearing aid, an in-the-ear (ITE) hearing aid, such as an in-the-ear (ITC) hearing aid, a complete-in-the-canal (CIC) hearing aid, hearing glasses, or a pocket hearing aid. Alternatively, the hearing aid is a behind-the-ear (BTE) hearing aid, which is worn behind the ear.

[0008] The hearing aid is designed and configured to be worn on the human body. In other words, the hearing aid preferably includes a retention device that allows it to be attached to the human body. If the hearing aid is a hearing assistance device, it is designed and configured to be placed, for example, behind the ear or within the ear canal. In particular, the hearing aid is wireless and designed and configured to be inserted, at least partially, into the ear canal.

[0009] The hearing aid includes a microphone for capturing sound. Specifically, when in operation, the microphone captures ambient sound, i.e., sound waves, or at least a portion thereof. The microphone is advantageously located, at least partially, within the hearing aid's housing and is thus at least partially protected. The microphone is suitably an electromechanical transducer. For example, the microphone may have a single microphone unit or several microphone units that interact with each other. Each microphone unit advantageously has a diaphragm that is set into vibration by sound waves, and these vibrations are converted into an electrical signal by a suitable recording device, such as a magnet moving within a coil.Alternatively, the microphone units are designed capacitively, utilizing the fact that an applied electrical voltage changes when the distance between the diaphragm and a static surface of the microphone unit changes. In this case, the electrical voltage is applied specifically between the diaphragm and the static surface. The microphone units are preferably designed omnidirectionally. In this or another way, it is at least possible to generate or at least provide an input signal using the microphone, based on the sound incident on the microphone, namely, in particular, ambient sound.

[0010] Furthermore, the hearing aid has a receiver for outputting a signal. The output signal is, in particular, an electrical signal, and may be, for example, digital or, more appropriately, analog. The receiver is preferably an electromechanical transducer, such as a loudspeaker. Depending on the design of the hearing aid, in its intended state, the receiver is at least partially positioned within the ear canal of a user of the hearing aid, i.e., a person also referred to as the wearer, or at least acoustically connected to it. The hearing aid primarily serves to output the signal via the receiver, thereby generating a corresponding sound. In other words, the main function of the hearing aid is preferably to output the signal.

[0011] The hearing aid also includes a signal processing unit by means of which the microphone and the receiver are connected. Advantageously, the hearing aid has a signal processor that, for example, forms the signal processing unit or is at least a component thereof. The signal processor is, for example, a digital signal processor (DSP) or implemented using analog components. The signal processor, or at least the signal processing unit, is used in particular to adjust the input signal generated by the microphone. At a minimum, the signal processing unit is suitable for this purpose, and in particular, is designed and configured for it. Advantageously, an analog-to-digital converter (ADC) is arranged between the microphone and the signal processing unit, for example, the signal processor, provided the signal processor is designed as a digital signal processor.Preferably, the hearing aid also includes an amplifier, or the amplifier is at least partially formed by the signal processing unit. For example, the amplifier is connected upstream or downstream of the signal processor in terms of signal processing.

[0012] The method involves providing the input signal. Specifically, the sound incident on the microphone is captured to generate the input signal. In other words, the microphone provides the input signal. Preferably, the input signal is based on the incident sound. Alternatively, the hearing aid may have a communication device for receiving the input signal. This signal could be generated by a separate device, such as a mobile phone, and transmitted to the hearing aid. In this case, the communication device operates, for example, according to a Bluetooth standard. Alternatively, or in combination with this, the communication device may be suitable for inductively receiving the input signal.

[0013] In a further step, a signal component is selected from the input signal. This signal component has a specific frequency. For example, the signal component may comprise only a single frequency or, more preferably, several frequencies, so that the signal component has a specific frequency band. This simplifies its processing. The frequency bands are advantageously predefined, e.g., according to the length of the (temporal) windows used for frequency analysis. In particular, the frequency bands are defined by means of a filter bank. Preferably, however, the frequencies are arranged directly adjacent to each other. In summary, the signal component is a part of the input signal and has the specified frequency and a specific amplitude.

[0014] In a further step, another signal is provided, which has a further specific frequency. Advantageously, this further signal has a corresponding frequency band as its further specific frequency, i.e., several frequencies that are directly adjacent to each other. This further signal is preferably relatively narrowband. The further signal also has a further specific amplitude. This further specific frequency differs from the initial specific frequency. Consequently, this further specific frequency is also not part of the potential frequency band of the signal component, if the frequency band is used as the specific frequency.

[0015] In a further step, an output signal is generated based on the signal component and the additional signal. Consequently, the output signal is based at least on the signal component and the additional signal, so that if the signal component and / or the additional signal are changed, the output signal is also changed. In particular, the signal component and the additional signal are combined to generate the output signal. For example, the signal component and / or the additional signal are processed before being combined into the output signal. Preferably, further components, especially from the input signal, are included in the output signal, so that the output signal expediently comprises essentially all components of the input signal, with the individual components being processed in particular. For this purpose, the signal processor is expediently configured according to a set of parameters.The parameter set specifies amplification in different frequency ranges, so that the input signal is processed according to certain specifications, especially depending on the hearing loss of the hearing aid wearer.

[0016] In a further step, the output signal is played back through the headphones, thus creating a sound. In other words, sound waves are generated. The sound corresponds, at least partially, to the signal component and the other signal. Consequently, if the signal component and / or the other signal changes, the sound also changes.

[0017] In its intended state, the hearing aid is preferably located at least partially in the user's ear canal, or at least, in its intended state / during intended use, the sound is introduced into the user's ear canal. There, the sound encounters the user's basilar membrane, which serves to capture the sound. In summary, the hearing aid is designed in such a way that, in its intended state, the sound is introduced into the user's ear canal and encounters the basilar membrane. Hair cells, particularly the outer hair cells, are located there and are set into vibration by the sound. The basilar membrane has different areas, each corresponding to a different frequency.When sound waves strike the ear, they primarily cause the hair cells in the ear to vibrate, specifically those corresponding to the frequency of the sound waves. In other words, the hearing aid is ideally designed so that, when functioning correctly, the sound is directed into the user's ear canal, causing the eardrum to vibrate. This vibration, in turn, causes the fluid in the cochlea to move via a coupling mechanism in the middle ear. The movement of this fluid in the cochlea then moves the basilar membrane, to which both inner and outer hair cells are attached. These hair cells are connected to the auditory system in the brain via nerve fibers and transform this mechanical movement into nerve impulses.

[0018] If the vibration has an amplitude above a specific hearing threshold, the corresponding nerves are stimulated, making the sound at that frequency conscious to the user. In other words, the hair cells are set into vibration to stimulate the associated nerves. In summary, the basilar membrane enables the user to selectively perceive sound at different frequencies.

[0019] The outer hair cells are not directly involved in transmitting sound to the brain; that task falls to the inner hair cells. The outer hair cells primarily serve to amplify (or even reduce, if necessary) movement of the basilar membrane. Small movements of the basilar membrane are amplified by the outer hair cells and strongly limited in their spatial extent (and thus in frequency), resulting in an amplified, but very narrowband, movement of the basilar membrane. This amplified movement is then registered by the inner hair cells and relayed to the brain.

[0020] In cases of hearing loss, the number of hair cells is reduced. Consequently, the nerves are also stimulated to a lesser degree, sometimes resulting in no stimulation at all. While the outer hair cells may vibrate slightly, this is insufficient to stimulate the corresponding nerves. Furthermore, the reduced number of hair cells eliminates the ability for them to interact with each other, meaning that when sound is emitted, hair cells in different areas are stimulated. As a result, frequency-selective hearing is no longer fully possible for the individual.

[0021] The subsequent signal is designed such that, when the hearing aid is used as intended, first and second time intervals are generated. Specifically, these time intervals are designed to alternate. In other words, each first time interval is followed by a second time interval, and vice versa. Preferably, all first time intervals and / or all second time intervals are of the same length. For example, the length of the first time intervals is equal to the length of the second time intervals, or their lengths are different from each other.

[0022] During the initial time intervals, the hair cells associated with a specific frequency are stimulated due to interference. Specifically, the portion of the sound based on the signal component interferes with the portion of the sound based on the additional signal. In particular, during these initial time intervals, the two sound components constructively overlap in this region. Consequently, the hair cells are stimulated more intensely in this area, at least compared to when the additional signal is not part of the original signal.

[0023] During the first time intervals, however, the hair cells associated with this area are not stimulated due to interference. In other words, even during the second time intervals, sound corresponding to the signal component is introduced, but the hair cells are not stimulated. Specifically, during the second time interval, the two sound components interfere destructively in this area.

[0024] In summary, the presence of the additional signal leads to increased stimulation of the hair cells associated with a specific frequency during the first time intervals, while these hair cells are not stimulated during the second time intervals. Thus, during the first time intervals, the hair cells are set into vibration such that the amplitude of the vibration is greater than the respective hearing threshold. During the second time intervals, however, the amplitude is less than the associated hearing threshold.

[0025] As a result of the process, if the signal component was present, the associated hair cells were alternately stimulated, i.e., a corresponding

[0026] Stimulation of the corresponding nerves allows the user to register a change in stimulation, thus facilitating the perception of the signal component and the sound based on it. This method does not require comparatively extensive amplification, reducing both the strain on the user and the energy consumption of the hearing aid compared to other methods. Furthermore, the method essentially only stimulates the hair cells associated with the specific frequency, enabling the user to distinguish the sound based on the signal component from other sound components with relative accuracy. In other words, the method allows the user to differentiate individual frequencies, thereby improving spectral resolution and enhancing sound intelligibility.

[0027] Introducing additional external signals to create this superposition can lead to less masking and thus better selectivity, because the signal information is "cleaner" in some time intervals (and "more blurred" in others). Furthermore, the brain may be able to use the moments of clarity to extract more information from the clear gaps.

[0028] In this process, the user is not a component of the process; however, the provision of the additional signal is expediently adapted to the user. In summary, the additional signal is adapted, in particular, depending on the user or at least a typical position of the hearing aid relative to the basilar membrane. Therefore, the position of the respective interferences, especially the fully constructive / destructive interference of the sound waves based on the signal component and the additional signal, always occurs within the desired area of ​​the basilar membrane.

[0029] For example, the method is performed in the time domain. However, it is particularly preferred that at least part of the method involves a frequency analysis, for which, for example, a Fourier transform is used. Thus, the method is particularly preferably performed at least partially in the frequency domain. Advantageously, the signal processing unit includes a filter bank by means of which the signal component is determined. Here, the filter bank is, for example, designed as a linear or logarithmic filter bank.

[0030] For example, the signal component is always selected in the same way. Thus, a comparatively extensive adjustment of the hearing aid to different users is essentially unnecessary. However, it is particularly preferred that the signal component be selected depending on the user's hearing loss. Here, the hearing loss, preferably a reduction in the user's sensitivity in certain frequency ranges, is stored in the hearing aid, expediently in the signal processing unit. The hearing loss is determined, for example, in a separate procedure, such as by an audiologist. Due to the adjustment depending on the hearing loss, corresponding interference preferably occurs in an area of ​​the basilar membrane where the hair cells or their number is reduced.In contrast, the formation of corresponding interference patterns is less pronounced in areas that still have a comparatively high number of hair cells. Thus, information contained in the input signal is preserved, which would otherwise be at least partially distorted. This increases its intelligibility.

[0031] The signal component is only selected if its amplitude exceeds a certain threshold. If the amplitude is lower than the threshold, the signal component is present in the input signal primarily due to background noise and / or interference. Since the signal component is not selected in this case, the background noise is not amplified and is therefore essentially imperceptible to the user. This increases comfort.

[0032] For example, only a single signal component is selected. However, it is particularly preferred to select multiple signal components, each with a different specific frequency. The output signal is then generated based on all selected components. In particular, there is a comparatively large gap between the specific frequencies. Thus, different frequency ranges are subjected to correspondingly amplified or suppressed excitation, making the different frequencies perceptible to the user. This further enhances comfort. For example, the first and second time windows assigned to the different signal components may be simultaneous, or they may be staggered in time.

[0033] For example, the additional signal is selected from the input signal and appropriately adjusted. Thus, the corresponding interference occurs only when the input signal already contains the additional signal. Preferably, the additional signal is generated synthetically, for example using a synthesizer, or it is stored in memory. This ensures that the interference occurs regardless of whether the additional signal is present in the input signal and regardless of any temporal changes in the additional signal within the input signal. Therefore, the interference always occurs in the same way, which increases user convenience.

[0034] In another implementation, the secondary signal is preferentially selected from the input signal, and its phase is specifically adjusted. Depending on the phase, this results in constructive or destructive interference. If this method allows for the targeted manipulation of the phases of the individual signal components, the correct "secondary signal" can be selected and manipulated more precisely to generate the desired constructive / destructive intervals at the desired frequency.

[0035] Regardless of how the additional signal is provided, it is advantageous to adjust its phase to create the desired interference. Alternatively or in combination, the amplitude is adjusted accordingly. Preferably, the amplitude and / or frequency of the additional signal is adjusted depending on the user's hearing loss and / or the specific frequency, particularly if several signal components with different specific frequencies are selected.

[0036] For example, only a single additional signal is provided. This reduces the number of interferences and simplifies the identification of individual interferences, requiring comparatively few hardware resources to perform the procedure. However, providing multiple additional signals is particularly preferred. In this case, all of these additional signals are used to generate the output signal. This simplifies the creation of interferences at the desired locations, meaning that only the excitation of the hair cells in the respective area is amplified or prevented. Furthermore, the multiple additional signals also make it possible to influence the length of the time windows, allowing the excitation of the hair cells to be enhanced according to a specific requirement. Consequently, the signal component, and thus the resulting sound, can be perceived more effectively by the user.Preferably, several signal components are present, with each of the signal components being expediently assigned at least one of the further signals.

[0037] For example, the amplitude of the signal component is not changed. However, it is particularly preferred that it is additionally adjusted, preferably depending on the user's hearing loss. Specifically, the adjusted signal component is added to the output signal so that the output signal contains only the adjusted signal component. In other words, the output signal is generated based on the adjusted signal component. This makes it possible to further enhance the formation of interference and consequently increase the length of the initial time windows during which a comparatively strong excitation of the corresponding hair cells occurs. Thus, the signal component is relatively easily perceived by the user. Alternatively or in combination with this, the phase of the signal component is adjusted accordingly. In particular, the signal component is adjusted as a function of frequency, preferably depending on the user.As a result, it is also possible to compensate for other causes of hearing loss using the procedure, thus further increasing user comfort and expanding the range of applications for the hearing aid.

[0038] For example, the deviation of a specific frequency from another specific frequency is constant, i.e., static. In other words, if the specific frequency is predetermined, particularly due to hearing loss, the other specific frequency is also predetermined. Consequently, determining the resulting interference is simplified. Alternatively, the deviation between the specific frequency and the other specific frequency is adjusted depending on a parameter. In other words, the deviation is not static, and it is possible, for example, that the other specific frequency is lower or higher than the specific frequency depending on the parameter. Thus, the length of the first / second time windows is also changed depending on the parameter. The presence of background noise and / or an operating mode of the hearing aid are used as parameters, for example.

[0039] For example, the additional signal is always provided. This makes the hearing aid's behavior predictable for the user. However, the additional signal is preferably not provided if the signal component is classified as belonging to background noise. In other words, the input signal is first classified to determine whether the signal component is caused by background noise. In this case, the additional signal is not generated, meaning the background noise is either not perceptible to the user or only to a reduced degree. This increases user comfort. Conversely, the additional signal is provided if the signal component is classified as not belonging to the background noise, and specifically as a desired sound or part of the desired sound. This makes the desired sound more perceptible to the user.

[0040] A hearing aid can be, for example, a headset or, more commonly, a hearing aid device. For instance, a hearing aid device might be a receiver-in-the-canal (RIC) hearing aid, an in-the-ear (ITC) hearing aid, a complete-in-the-canal (CIC) hearing aid, hearing glasses, or a pocket hearing aid. Alternatively, a hearing aid can be a behind-the-ear (BTE) hearing aid, which is worn behind the ear.

[0041] The hearing aid comprises a microphone and a receiver, which are connected via a signal processing unit. The hearing aid operates according to a method in which an input signal is provided, preferably via the microphone. A signal component of the input signal with a specific frequency is selected, and a further signal with another specific frequency is provided. An output signal is generated based on the signal component and the further signal, and the output signal is delivered via the receiver, thus producing sound. The further signal is designed and, for example, generated / adapted in such a way as to create first and second time intervals. During the first time intervals, hair cells located in a region of the user's basilar membrane corresponding to a specific frequency are stimulated due to interference.During the second time interval, the hair cells are not stimulated. For example, the procedure is carried out at least partially using the signal processing unit. Thus, the signal processing unit is suitable, and in particular designed and configured, to carry out at least part of the procedure.

[0042] The further training and advantages explained in connection with the procedure can also be applied analogously to the hearing aid and vice versa.

[0043] An embodiment of the invention is explained in more detail below with reference to a drawing. The drawing shows: Fig. 1 schematically a hearing aid, Fig. 2 a method for operating the hearing aid, Fig. 3 a simplified frequency spectrum of an input signal used in the method, Fig. 4 a simplified frequency spectrum of an output signal created by the method, Fig. 5 a sound wave created from one signal component and one created from another signal, and Fig. 6 the superposition of the two sound waves.

[0044] Corresponding parts are marked with the same reference symbols in all figures.

[0045] In Figure 1A schematic representation of a hearing aid 2 is shown, designed and configured to be worn behind the ear of a wearer (user). In other words, it is a behind-the-ear hearing aid. The hearing aid 2 comprises a housing 4 made of plastic. Inside the housing 4 is a microphone 6 with two microphone units 8, each in the form of an electromechanical transducer, which are omnidirectional. By changing the time delay between the acoustic signals detected by the omnidirectional microphone units 8, it is possible to change the directional characteristic of the microphone 6, thus creating a directional microphone.

[0046] The two microphone units 8, i.e., the microphone 6, are signal-technically coupled to a signal processing unit 10, which comprises an amplifier circuit (not shown) and a signal processor. The signal processing unit 10 is further formed by circuit elements such as electrical and / or electronic components. The signal processor is a digital signal processor (DSP) and is signal-technically connected to the microphone units 8 via an analog-to-digital converter (ADC) (not shown).

[0047] A receiver 12 is signal-coupled to the signal processing unit 10. Thus, the microphone 6 and the receiver 12 are signal-connected via the signal processing unit 10. During operation, the receiver 12, which is an electromechanical transducer, converts an (electrical) signal provided by the signal processing unit 10 into sound waves. These are introduced into a sound tube 14, one end of which is attached to the housing 4. The other end of the sound tube 14 is enclosed by a dome 16, which, in its intended state, is positioned in the ear canal 18 of a user of the hearing aid 2, i.e., the wearer of the hearing aid 2.

[0048] The basilar membrane 20, which has several areas 22, is located in the user's ear canal 18. Each of these areas 22 contains hair cells, known as outer hair cells, which are not shown in detail. When sound waves enter the ear canal 18, they cause the hair cells to vibrate. The maximum amplitude of the vibration develops in the area 22 corresponding to the frequency of the sound waves. The amplitude of the resulting vibration also depends on the amplitude of the sound wave. If the sound waves have only a single frequency, the maximum occurs in only one of the areas 22. If, however, the sound wave has a different frequency, the maximum develops in a different area 22. If the amplitude is greater than the respective hearing threshold, the nerves associated with that area 22 are stimulated, allowing the user to perceive the sound wave.Otherwise, the sound wave will not be perceived.

[0049] When some hair cells are lost, the maximum achievable amplitude of the vibration is reduced, so that stimulation of the corresponding nerve cells only occurs at a comparatively large amplitude of the respective sound wave. Furthermore, due to the reduced number of hair cells, the interaction between them is altered, so that the maximum is not only present in the range associated with the respective frequency, but also in surrounding areas.22 Therefore, the user does not perceive just a single sharp frequency, which reduces intelligibility. This occurs, for example, when the sound is below the hearing threshold, but also at levels above the hearing threshold. Since the outer hair cells contribute to ensuring good frequency selectivity, it is their loss that leads to a broader excitation of the basilar membrane.20 Hearing loss most commonly affects the outer hair cells.Because the outer hair cells have an active amplification mechanism, the basilar membrane excitation exhibits non-linear behavior. If the inner hair cells are still present, processing in the inner ear is more linear in these areas.

[0050] The signal processing unit 10 is powered by a battery 24 located in the housing 4. A portion of the electrical energy is directed from the signal processing unit 10 to the microphone 6 and the earpiece 12. In doing so, the signal processing unit 10 at least partially generates a signal in Figure 2The described procedure 26 is carried out to operate the hearing aid 2. In other words, the hearing aid 2 is operated according to procedure 26. In a first step 28, an input signal 30 is provided. The input signal 30 is generated, for example, by means of the microphone 6 and routed to the signal processing unit 10, so that it is received by the signal processing unit 10.

[0051] In a subsequent second step 32, a frequency analysis of the input signal 30 is performed, for which a filter bank 34 of the signal processor of the signal processing unit 10 is used. Here, the individual frequencies of the input signal 30 and their corresponding amplitudes are determined, so that a frequency spectrum is created. Furthermore, a classification of the individual components of the frequency spectrum is carried out.

[0052] In Figure 3An example of a corresponding frequency spectrum of the input signal 30 is shown. This signal has two signal components 36 that are present due to a useful noise, for example, speech in the sound detected by the microphone 6. Furthermore, the input signal 30 has a residual component 38, which in the example shown is also due to speech present in the sound detected by the microphone 6.

[0053] The two signal components 36 each have a specific frequency 40, namely a frequency band, whereby the two specific frequencies 40 assigned to the different signal components 36 are different. In the areas 22 of the basilar membrane 20 assigned to these two specific frequencies 40, there is a reduction in the user's hair cells, which causes hearing loss. The reduction is greater in one of the two areas 22 than in the other. The frequency of the remaining component 38, however, corresponds to one of the areas 22 of the basilar membrane 20 in which there is no or only a slight reduction in hair cells. Thus, the user's hearing is not impaired at this frequency.

[0054] The two signal components 36 are selected. In other words, the signal components 36 are selected depending on the user's hearing loss, whereas the remaining component 38 is not selected, since there is no hearing loss at the assigned frequency. In summary, several, namely two, signal components 36 are selected, each with a specific frequency 40, and each of which is a component of the input signal 30.

[0055] In a third step 42, two further signals 44 are synthetically generated and thus provided for each of the selected signal components 36. Each of these further signals 44 has a further specific frequency 46. In summary, several further signals 44, namely four, are provided, with two of them being assigned to each of the two signal components 36. The further specific frequencies 46 of the respective further signals 44 differ from the specific frequency 40 of the respective assigned signal component 36, whereby the deviation between the specific frequency 40 and the two further specific frequencies 46 is adjusted depending on a parameter. In the example shown, the number of remaining components 38 is used as a parameter, or, for example, an ambient volume and / or the presence of background noise.It is also possible to determine the respective deviation based on the user's hearing loss.

[0056] In the example shown, the additional specific frequencies 46 directly follow the specific frequency 40 of the one assigned signal component 36, such that the frequency band of the signal component 36 is framed by the frequency bands of the assigned additional signals 44, and these follow directly one another. Consequently, one of the additional specific frequencies 46 is higher than the assigned specific frequency 40, and the other additional specific frequency 46 is lower.

[0057] The frequency band of one of the other signals 44 directly adjoins the other signal component 36. The frequency band of the other signal 44, however, is slightly offset from the frequency band of the associated signal component 36.

[0058] In the third step 42, the amplitude of the two signal components 36 are adjusted depending on the user's hearing loss. In the example shown, the amplitude of signal component 36 of the input signal 30 was essentially the same. Due to the adjustment depending on the user's hearing loss, in the example shown, the amplitude of one of the two signal components 36 is larger after the adjustment, although both amplitudes have been increased.

[0059] In a subsequent fourth step 48, the adjusted signal components 36, the other signals 44, and the remaining component 38 are combined to form an output signal 50, so that the output signal 50 is created based on the adjusted signal components 36 and the other signals 44. Thus, the output signal 50 exhibits the in Figure 4 The displayed frequency spectrum is shown.

[0060] In a subsequent fifth step 52, the output signal 50 is routed to the receiver 12, through which the sound is emitted into the ear canal. Due to the intended use of the hearing aid 2, the sound is introduced into the ear canal 18. Consequently, the output signal 50 is emitted via the receiver 12, thus generating the sound. Specifically, the output signal 50 is first converted into an analog signal, so that the analog output signal 50 is emitted. The sound is composed of different sound waves and corresponds to the (adapted) signal component 36 as well as the other signals 44. In a variant not shown in detail, the output signal 50 is also amplified by means of an amplifier.

[0061] The sound waves strike the user's basilar membrane 20, thus stimulating the areas 22. The additional signals 44 were generated such that first time intervals 54 and second time intervals 56 were created. For this purpose, the further specified frequencies 46, the phases, and the amplitudes of the additional signals 44 were selected accordingly. The first time intervals 54 alternate with the second time intervals 56. During the first time intervals 54, the hair cells of the areas 22, which are assigned to the specified frequencies 40 of the signal components 36, are stimulated due to interference between the sound waves corresponding to the signal components 36 and the sound waves corresponding to the additional signals 44. In contrast, during the second time intervals 56, the hair cells assigned to the same area 22 are not stimulated.

[0062] In Figure 5To illustrate the principle, two sound waves 58 are shown, each with a different frequency. For the sake of simplicity, the amplitude of both sound waves 58 is chosen to be the same.

[0063] The superposition of the two sound waves 58, i.e. the resulting sound 60, is in Figure 6 The interference results in the first time intervals 54, during which the magnitude of the resulting sound 60 is greater than a hearing threshold 62. In this case, the hair cells vibrate sufficiently to stimulate the associated nerves. In other words, the hair cells are stimulated. If, on the other hand, the resulting sound 60 is less than the hearing threshold 62, stimulation does not occur, and one of the second time intervals 56 is formed. Due to the alternating stimulation of the associated hair cells, the sound is perceived relatively accurately by the user.

[0064] The additional signals 44 are designed such that the hair cells of the area 22 assigned to the respective specific frequency 40 are stimulated, but not adjacent areas 22. Thus, the specific frequencies 40, and therefore the signal components 36, are perceived with comparative precision by the user and can be assigned to the specific frequency 40. Consequently, the spectral resolution during hearing is increased for the user, despite the loss of hair cells.

[0065] The signal components 36 are selected depending on the user's hearing loss. In other words, the specific frequencies 40 are assigned to those areas 22 where there is a loss of hair cells. However, if in the second step 32 the respective signal component 36 is classified as belonging to background noise, the corresponding additional signals 44 are not generated. Thus, the background noise is not perceived more intensely by the user, which increases comfort.

[0066] The invention is not limited to the embodiment described above. Rather, other variants of the invention can also be derived by a person skilled in the art without departing from the subject matter of the invention. In particular, all individual features described in connection with the embodiment can also be combined with one another in other ways without departing from the subject matter of the invention. Reference symbol list

[0067] 2 Hearing aid 4 Housing 6 Microphone 8 Microphone unit 10 Signal processing unit 12 Receiver 14 Sound tube 16 Dome 18 Ear canal 20 Basilar membrane 22 Area 24 Battery 26 Procedure 28 First step 30 Input signal 32 Second step 34 Filter bank 36 Signal component 38 Residual component 40 Specific frequency 42 Third step 44 Additional signal 46 Additional specific frequency 48 Fourth step 50 Output signal 52 Fifth step 54 First time interval 56 Second time interval 58 Sound waves 60 Resulting sound 62 Hearing threshold

Claims

1. A method (26) for operating a hearing aid (2) comprising a microphone (6) and a receiver (12) that are signal-linked by means of a signal processing unit (10), in which - an input signal (30) is provided, - a signal component (36) of the input signal (30) having a specific frequency (40) is selected, - a further signal (44) having a further specific frequency (46) is provided, - an output signal (50) is generated based on the signal component (36) and the further signal (44), and - the output signal (50) is output by means of the receiver (12) so that a sound is generated, wherein the further signal (44) is configured such that first time intervals (54) and second time intervals (56) result, wherein during the first time intervals (54) hair cells that are located in a region (22) of a basilar membrane (20) of a user that is associated with the specific frequency (40) are assigned,are excited due to interference, and during the second time intervals (56) no excitation of the hair cells occurs., 2. Method (26) according to claim 1, characterized by that the signal component (36) is selected depending on the user's hearing loss.

3. Method (26) according to claim 1 or 2, characterized by that several signal components (36) can be selected.

4. Method (26) according to one of claims 1 to 3, characterized by that the further signal (44) is generated synthetically.

5. Method (26) according to one of claims 1 to 4, characterized by that several further signals (44) are provided.

6. Method (26) according to one of claims 1 to 5, characterized by that an amplitude of the signal component (36) is adjusted depending on a hearing loss of the user.

7. Method (26) according to one of claims 1 to 6, characterized by thatthe deviation between the determined frequency (40) and the further determined frequency (46) is adjusted depending on a parameter.

8. Method (26) according to one of claims 1 to 7, characterized by that the further signal (44) is not provided if the signal component (36) is classified as belonging to an interference noise.

9. Hearing aid (2) comprising a microphone (6) and a receiver (12) which are signal-technically connected by means of a signal processing unit (10), and which is operated according to a method (26) according to one of claims 1 to 8.

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