Method for operating a hearing device and hearing device

Abstract

The invention relates to a method (26) for operating a hearing device (2), comprising a microphone (6) and an earpiece (12), which are signalling by means of a signal processing unit (10). An input signal (30) is provided and a signal component (36) of the input signal having a particular frequency (40) is selected. A further signal (44) having a further specific frequency (46) is provided, and an output signal (50) is generated as a function of the signal component and the further signal. The output signal is output by means of the earpiece, thereby producing a sound. The further signal is designed to generate a first time interval (54) during which hair cells associated in a region (22) of the basement membrane (20) of the user associated with the specific frequency are excited due to the interference and a second time interval (56) during which hair cells are not excited. The invention also relates to a hearing device.

Description

Technical Field

[0001] The invention relates to a method for operating a hearing device and a hearing device. The hearing device comprises a microphone and an earpiece, which are connected via signal technology by means of a signal processing unit. Background Art

[0002] People who suffer from hearing loss usually use a hearing aid, which is a hearing device. Here, the ambient sound is usually converted into an electrical (audio / sound) signal by means of a microphone, i.e. an electromechanical sound converter, so that an input signal is provided. The input signal is processed by means of an amplifier circuit and guided into the ear canal of the person by means of a further electromechanical converter in the form of a receiver. Furthermore, the acquired input signal is usually processed depending on the hearing loss, for which purpose a signal processing unit is usually used, which can include an amplifier circuit.

[0003] To this end, it is usually first determined by an audiologist which frequencies of the unchanged input signal the user can perceive only to a reduced degree. For these frequencies, the corresponding amplitudes are then increased by means of a signal processing unit during normal use of the hearing instrument, so that these components of the input signal are amplified. However, it is also possible that the user can no longer perceive certain frequencies, usually relatively high frequencies, at all. In this case, the corresponding components of the input signal are shifted to lower frequencies by means of a signal processing unit, which is also called compression.

[0004] In all of these methods, only the symptoms are alleviated or modified. However, the physiological changes of the user that are the basis for hearing loss are not taken into account. Therefore, the performance of these methods is limited in principle. Summary of the invention

[0005] The object of the present invention is to specify a particularly suitable method for operating a hearing instrument and a particularly suitable hearing instrument, wherein in particular the performance is increased.

[0006] The above-mentioned technical problem is solved with respect to the method and with respect to the hearing device by the features of the invention. Advantageous embodiments and configurations are the subject of the following description.

[0007] The method is used to operate a hearing device. For example, the hearing device is an earphone or includes an earphone, and the hearing device is, for example, a headset. However, it is particularly preferred that the hearing device is a hearing aid device. The hearing aid device is used to support people who suffer from hearing loss. In other words, the hearing aid device is a medical device used to compensate for partial hearing loss, for example. The hearing aid device is, for example, a "receiver-in-the-canal" hearing aid device (RIC; external ear hearing aid device), an in-ear hearing aid device, such as an "in-the-ear" hearing aid device, an "in-the-canal" hearing aid device (ITC) or a "complete-in-canal" hearing aid device (CIC), hearing glasses or a pocket hearing aid device. Alternatively, the hearing aid device is a behind-the-ear hearing aid device worn behind the auricle.

[0008] The hearing device is designed and configured to be worn on a person's body. In other words, the hearing device preferably comprises a retaining device, by means of which it can be fixed on a person's body. If the hearing device is a hearing aid device, the hearing device is designed and configured to be arranged, for example, behind the ear or inside the ear canal. In particular, the hearing device is wireless and is designed and configured to be at least partially inserted into the ear canal.

[0009] The hearing device comprises a microphone for collecting sound. In particular, the ambient sound, i.e. the sound waves or at least a part thereof, is collected by means of the microphone during operation. The microphone is suitably arranged at least partially inside the housing of the hearing device and is therefore at least partially protected. The microphone is suitably an electromechanical sound converter. The microphone has, for example, only a single microphone unit or a plurality of microphone units that interact with each other. Each microphone unit suitably has a membrane that is vibrated by means of sound waves, wherein the vibration is converted into an electrical signal by means of a corresponding receiving device, such as a magnet moving in a coil. As an alternative thereto, the microphone unit is designed to be capacitive and utilizes the fact that the applied voltage changes when the distance of the membrane to the static surface of the microphone unit changes. Here, the voltage is applied in particular between the membrane and the static surface. The microphone unit is preferably designed to be omnidirectional. In this way or in another way, at least an input signal can be generated or at least provided by means of the microphone, which input signal is based on the sound, i.e. in particular the ambient sound, reaching the microphone.

[0010] In addition, the hearing device has an earpiece for outputting an output signal. In this case, the output signal is in particular an electrical signal and is designed, for example, to be digital or, where appropriate, analog. The earpiece is preferably an electromechanical sound converter, for example a loudspeaker. Depending on the design of the hearing device, in a normal state, the earpiece is at least partially arranged inside the ear canal of a user of the hearing device, also referred to as a wearer, or is at least acoustically connected to the ear canal. The hearing device is in particular mainly used to output the output signal by means of the earpiece, wherein a corresponding sound is generated. In other words, the main function of the hearing device is to output the output signal.

[0011] Furthermore, the hearing device comprises a signal processing unit, by means of which the microphone and the receiver are connected via signal technology. The hearing device preferably has a signal processor, which 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 is implemented by means of analog components. By means of the signal processor or at least the signal processing unit, in particular an input signal generated by means of the microphone is adjusted. At least the signal processing unit is suitable for this, in particular is provided and configured for this. If the signal processor is designed as a digital signal processor, it is suitable to arrange an A / D converter between the microphone and the signal processing unit, for example the signal processor. It is particularly preferred that the hearing device additionally comprises an amplifier, or that the amplifier is at least partially formed by means of the signal processing unit. For example, the amplifier is connected upstream or downstream of the signal processor via signal technology.

[0012] The method is configured to provide an input signal. For this purpose, in particular, the sound arriving at the microphone is collected to provide the input signal. In other words, the input signal is provided by means of the microphone. Therefore, it is preferred that the input signal is based on the arriving sound. As an alternative, the hearing device has, for example, a communication device, by means of which the input signal is received. The input signal is, for example, generated by a separate device, such as a mobile phone, and transmitted to the hearing device. In this case, the communication device operates, for example, according to the Bluetooth standard. As an alternative or in combination, the communication device is suitable for receiving the input signal in an inductive manner.

[0013] In a further working step, a signal component is selected from the input signal. Here, the signal component has a specific frequency. For example, the signal component comprises only a single frequency, or particularly preferably comprises a plurality of frequencies, so that the signal component has a specific frequency band. Thus, the processing is simplified. It is suitable, for example, to predetermine the frequency band according to the length of the (time) window used for the frequency analysis. In particular, the frequency band is predetermined by means of a filter bank. However, it is preferred that these frequencies are arranged directly adjacent to each other. In short, the signal component is a component of the input signal and has a specific frequency and a specific amplitude.

[0014] In a further working step, a further signal is provided, which has a further specific frequency. It is suitable that the further signal has a corresponding frequency band, i.e. a plurality of frequencies as the further specific frequency, but the plurality of frequencies are directly adjacent to each other. Here, the further signal is preferably a relatively narrowband. In addition, the further signal has a further specific amplitude. The further specific frequency is different from the specific frequency. Therefore, if the frequency band is used as the specific frequency, the further specific frequency is also not a component of the possible frequency band of the signal component.

[0015] In a further working step, an output signal is generated based on the signal component and the further signal. Therefore, the output signal is based at least on the signal component and the further signal, so that when the signal component and / or the further signal changes, the output signal also changes. In particular, the signal component and the further signal are synthesized to generate the output signal. For example, before the signal component and the further signal are synthesized into the output signal, the signal component and / or the further signal are processed. It is particularly preferred that other components, in particular other components of the input signal, are also received into the output signal, so that the output signal is suitable to basically include all components of the input signal, wherein in particular the individual components are processed here. For this purpose, it is suitable to set the signal processor according to a parameter group. Here, the gain is predefined in different frequency ranges by means of the parameter group, so that the input signal is processed corresponding to specific predefined parameters, in particular according to the hearing loss of the wearer of the hearing device.

[0016] In a further working step, the output signal is outputted by means of a receiver, thereby generating a sound. In other words, a sound wave is generated. Here, the sound corresponds at least partially to the signal component and the further signal. Therefore, when the signal component changes and / or the further signal changes, the sound also changes.

[0017] Here, in the normal state, the hearing device is preferably at least partially located in the ear canal of the user, or at least in the normal state / during normal use, the sound is guided into the ear canal of the user. There the sound reaches the basilar membrane of the user for collecting the sound. In summary, the hearing device is particularly configured so that, in the normal state, the sound is guided into the ear canal of the user and reaches the basilar membrane there. There are hair cells, particularly so-called outer hair cells, which are vibrated by the sound. Here, the basilar membrane has different areas, which are associated with different frequencies. Here, when the sound arrives, the hair cells are mainly vibrated, which are associated with the following areas, the frequencies of which correspond to the sound, i.e., the sound waves. In other words, the hearing device is preferably configured so that, in the normal state, the sound is guided into the ear canal of the user, thereby vibrating the eardrum and also moving the fluid in the cochlea by coupling in the middle ear. The movement of the fluid in the cochlea produces the movement of the basilar membrane, to which both the inner hair cells and the outer hair cells are coupled. These hair cells are connected to the auditory system in the brain via nerve fibers and convert mechanical movements into nerve impulses.

[0018] When the vibration has an amplitude above the corresponding associated hearing threshold, the corresponding associated nerve is stimulated accordingly, so that the user perceives the sound with the corresponding frequency. In other words, in order to excite the hair cells, the hair cells are vibrated, thereby stimulating the associated nerves. In short, with the help of the basilar membrane, the user can collect sound in a frequency-selective manner.

[0019] Here, the outer hair cells are not directly involved in the conduction of sound to the brain, but the inner hair cells are. The outer hair cells are mainly used to amplify the movements of the basilar membrane (or even reduce them when they are not needed). Small movements of the basilar membrane are amplified by the outer hair cells and are strongly limited in local extension (and therefore in frequency), i.e. the basilar membrane performs an amplified, but very narrow-band movement. The inner hair cells then record this amplified movement and transmit it to the brain.

[0020] In the case of hearing loss, the number of hair cells decreases. Therefore, the nerves are also stimulated to a reduced extent, so that some are no longer stimulated. Although it is possible to make the outer hair cells vibrate slightly, this is not enough to stimulate the associated nerves. Due to the reduction in number, the hair cells do not influence each other either, so that when the sound arrives, hair cells in different areas are stimulated. Therefore, the user is no longer able to listen in a completely frequency-selective manner.

[0021] In this case, the further signal is designed such that, when the hearing device is used normally, a first time interval and a second time interval are generated. In particular, the time intervals are designed such that they alternate. In other words, each first time interval is followed by a second time interval, and vice versa. In this case, preferably all first time intervals have the same length and / or all second time intervals have the same length. In this case, for example, the length of the first time interval is the same as the length of the second time interval, or their lengths differ from each other.

[0022] During the first time interval, the hair cells associated with the specific frequency are excited due to the interference. In particular, the sound portion based on this signal component is disturbed by the sound portion based on the further signal. In particular, during the first time window, the two parts of the sound are constructively superimposed in this region. As a result, the hair cells are excited there in an amplified manner, at least in comparison to the case where the further signal is not a component of the output signal.

[0023] In contrast, during the first time interval, the hair cells associated with this region are not excited due to the interference. In other words, the sound corresponding to this signal component is also introduced during the second time interval, but the hair cells are not excited. In particular, during the second time window, these two parts of the sound are destructively superimposed in this region.

[0024] In summary, due to the presence of the additional signal, during the first time interval, the hair cells associated with a specific frequency are amplified and excited, while during the second time interval, these hair cells are not excited. Thus, during the first time window, the hair cells are vibrated so that the amplitude of the vibration is greater than the corresponding hearing threshold. In contrast, during the second time window, the amplitude is less than the associated hearing threshold.

[0025] Therefore, based on the method, when the signal component is present, the associated hair cells are alternately stimulated, i.e., the associated nerves are correspondingly stimulated, so that for the user, a change in the stimulation can be registered, which makes it easier to perceive the signal component or the sound based thereon. In this case, relatively large-scale amplification is not required, so that compared with other methods, on the one hand, the burden on the user is reduced, and on the other hand, the energy consumption of the hearing device is reduced. In addition, based on the method, essentially only the hair cells associated with a specific frequency are stimulated, so that for the user, it is possible to relatively accurately distinguish the sound based on the signal component from other components of the sound. In other words, based on the method, the user can distinguish between individual frequencies, so that its spectral resolution is improved, and thus the intelligibility of the sound for the user is improved.

[0026] Therefore, the introduction of external additional signals in order to produce the superposition can lead in particular to less masking and thus to better selectivity, since the signal information is "clearer" in different signal intervals (and "blurrier" in other signal intervals). In addition, the brain in particular can thereby use the clear moments in order to extract more information in the clear gaps.

[0027] In the method, the user is not part of the method, but the provision of the further signal is adapted to the user. In summary, the further signal is adapted, in particular, to the user or to at least one general position of the hearing device relative to the basilar membrane, so that the location of the corresponding interference, in particular the location of the complete constructive / destructive interference of the sound waves based on the signal component and the further signal, always occurs in the desired area of ​​the basilar membrane.

[0028] For example, the method is performed in the time domain. However, it is particularly preferred that a frequency analysis is at least partially performed for the performance of the method, for which purpose, for example, a Fourier transform is used. Therefore, it is particularly preferred that the method is at least partially performed in the frequency domain. The signal processing unit preferably comprises a filter bank, by means of which the signal components are determined. In this case, the filter bank is designed, for example, as a linear or logarithmic filter bank.

[0029] For example, the signal component is always selected in the same way. Therefore, a relatively large-scale adaptation of the hearing device to different users is basically not required. However, it is particularly preferred to select the signal component according to the hearing loss of the user. Here, the hearing loss, preferably the reduction in the sensitivity of the user in a certain frequency range, is in particular stored in the hearing device, preferably in the signal processing unit. Here, for example, the hearing loss is determined in a separate process, for example by an audiologist. Based on the adaptation according to the hearing loss, a corresponding interference is preferably generated in the following area of ​​the basilar membrane, that is, in this area, the number of hair cells or hair cells there is reduced. On the contrary, in areas that still have a relatively large number of hair cells, the corresponding interference is less strongly formed. Therefore, the information contained in the input signal is retained, which otherwise would be at least partially distorted. Therefore, its intelligibility is improved.

[0030] Particularly preferably, the signal component is selected only when its amplitude is greater than a certain threshold value. If the amplitude is less than the threshold value, the signal component is present in the input signal, in particular, only due to interfering noise and / or noise. Since the signal component is not selected in this case, the interfering noise is not present in the sound in an amplified manner, so that the user is substantially unable to perceive the interfering noise. As a result, the comfort level is increased.

[0031] For example, only a single signal component is selected. However, it is particularly preferred to select a plurality of signal components, wherein the signal components have different specific frequencies respectively. In this case, the output signal is generated according to all selected signal components. In this case, in particular, there are relatively large distances between these specific frequencies. Therefore, corresponding amplified excitation and non-excitation are performed in different areas, so that the user can perceive different frequencies. Therefore, the comfort is further improved. For example, in this case, the first and second time windows associated with different signal components are simultaneous, or the first and second time windows associated with different signal components are staggered in time with each other.

[0032] For example, the further signal is selected from the input signal and suitably adjusted accordingly. Thus, the corresponding interference is only carried out when the input signal already has the further signal. Particularly preferably, the further signal is generated synthetically, for example by means of a synthesizer, or the further signal is stored in a memory. Thus, the corresponding interference is carried out independently of whether the further signal is present in the input signal and independently of possible changes of the further signal in the input signal over time. Thus, the interference is always carried out in the same way, which increases the comfort of the user.

[0033] In another embodiment, the further signal is preferably selected from the input signal and the phase is adjusted in a targeted manner. In this case, constructive or destructive interference occurs depending on the phase. If the method shows a targeted manipulation of the phase of the individual signal components, in particular, the correct "further signal" can also be selected and manipulated more specifically in order to produce a constructive / destructive interval at the desired frequency.

[0034] The phase of the further signal is appropriately adjusted independently of the way in which the further signal is provided, so as to suitably generate the desired interference. As an alternative or in combination therewith, the amplitude is adjusted accordingly. In particular, if a plurality of signal components with different specific frequencies are selected, the amplitude and / or frequency of the further signal is preferably adjusted depending on the hearing loss of the user and / or on the specific frequency.

[0035] For example, only a single further signal is provided. As a result, the number of interferences is reduced and the determination of the individual interferences is simplified, so that relatively few hardware resources are required to carry out the method. However, it is particularly preferred to provide a plurality of further signals. In this case, all further signals are used to generate the output signal. In this way, the formation of interferences at the desired location is simplified, that is, the hair cells are only amplified in the corresponding area or are not excited. In addition, based on a plurality of further signals, the length of the time window can also be influenced, so that the hair cells can be excited in an improved manner corresponding to the corresponding predetermined parameters. As a result, the user can perceive the signal component, i.e. the sound on which it is based, in an improved manner. In this case, preferably a plurality of signal components are present, wherein each signal component is suitable for being associated with at least one of the further signals.

[0036] For example, the amplitude of the signal component is not changed. However, it is particularly preferred to additionally adjust the amplitude of the signal component, preferably in accordance with the hearing loss of the user. In particular, the adjusted signal component is added to the output signal, so that only the adjusted signal component is present in the output signal. In other words, the output signal is generated according to the adjusted signal component. Therefore, the formation of interference can be further strengthened and the length of the first time window can be increased, so that the associated hair cells are relatively strongly stimulated during this length of the first time window. Therefore, the user can perceive the signal component relatively well. As an alternative or in combination with it, the phase of the signal component is adjusted accordingly. Here, the signal component is adjusted, in particular in relation to the frequency, preferably in accordance with the user. Therefore, other causes of hearing loss can also be compensated for with the help of the method, so that the comfort for the user is further improved and the range of use of the hearing device is increased.

[0037] 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, in particular predetermined based on the hearing loss, then the other specific frequency is also predetermined. Thus, the determination of the interference generated is simplified. As an alternative thereto, 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 for example the other specific frequency can be smaller or larger than the specific frequency depending on the parameter. Thus, in particular, the length of the first / second time window is also changed depending on the parameter. For example, the presence of interfering noise and / or the operating mode of the hearing device are used as parameters.

[0038] For example, the further signal is always provided. Thus, the behavior of the hearing device is always predictable for the user. However, it is particularly preferred that the further signal is not provided when the signal component is classified as belonging to interfering noise. In other words, the input signal is first classified, wherein it is checked whether the signal component is due to interfering noise. In this case, the further signal is not generated, so that the interfering noise is not perceived by the user or is perceived only to a reduced extent. Thus, comfort for the user is improved. Conversely, the further signal is provided when the signal component is classified as not belonging to interfering noise, in particular as useful noise or part of useful noise. Thus, the useful noise can be better perceived by the user.

[0039] The hearing device is, for example, a headset or, more preferably, a hearing aid. For example, the hearing aid is a "receiver-in-the-canal" hearing aid (RIC; external ear hearing aid), an in-ear hearing aid, such as an "in-the-ear" hearing aid, an "in-the-canal" hearing aid (ITC) or a "complete-in-canal" hearing aid (CIC), hearing glasses or a pocket hearing aid. Alternatively, the hearing aid is a "behind-the-ear" hearing aid that is worn behind the auricle.

[0040] The hearing device comprises a microphone and an earpiece, which are connected by signal technology with the aid of a signal processing unit. The hearing device operates according to the method, in which an input signal is preferably provided with the aid of a module. A signal component of the input signal having a specific frequency is selected, and an additional signal having another specific frequency is provided. An output signal is generated according to the signal component and the additional signal, and the output signal is output with the aid of the earpiece, thereby generating sound. Here, the additional signal is designed and, for example, correspondingly generated / adjusted to generate a first time interval and a second time interval. During the first time interval, hair cells associated with a region of the basilar membrane of the user associated with the specific frequency are stimulated based on interference. During the second time interval, the hair cells are not stimulated. For example, the method is at least partially performed with the aid of a signal processing unit. Therefore, the signal processing unit is suitable for, in particular, is arranged and configured to, at least partially perform the method.

[0041] The embodiments and advantages described in conjunction with the method can also be transferred to the hearing instrument and vice versa. BRIEF DESCRIPTION OF THE DRAWINGS

[0042] The embodiments of the present invention are described in detail below with reference to the accompanying drawings. In the accompanying drawings:

[0043] Figure 1 schematically illustrates a hearing device,

[0044] Figure 2 A method for operating a hearing device is shown.

[0045] Figure 3 shows a simplified spectrum of the input signal used in the method,

[0046] Figure 4 shows a simplified spectrum of an output signal generated by means of the method,

[0047] Figure 5 shows the acoustic waves generated from the signal components and from the further signal, and

[0048] Figure 6 The superposition of two sound waves is shown.

[0049] Parts that correspond to one another are provided with the same reference symbols in all the figures. DETAILED DESCRIPTION

[0050] exist Figure 1 A hearing device 2 in the form of a hearing aid is schematically shown, which is arranged and configured to be worn behind the ear of a wearer (user, hearing device wearer, user). In other words, it is a behind-the-ear hearing aid. The hearing device 2 includes a housing 4, which is made of plastic. A microphone 6 with two microphone units 8 is arranged inside the housing 4, and these microphone units 8 respectively have the form of electromechanical sound converters and are designed to be omnidirectional. By changing the time shift between the acoustic signals collected by means of the omnidirectional microphone unit 8, the directional characteristics of the microphone 6 can be changed, thereby realizing a directional microphone.

[0051] The two microphone units 8, namely the microphone 6, are coupled to a signal processing unit 10 via signal technology, which includes an amplifier circuit and a signal processor, which are not shown in detail. In addition, the signal processing unit 10 is formed by means of circuit elements, such as electrical and / or electronic components. The signal processor is a digital signal processor (DSP) and is connected to the microphone unit 8 via a signal technology via an A / D converter, which is not shown in detail.

[0052] The receiver 12 is coupled to the signal processing unit 10 via signal technology. The microphone 6 and the receiver 12 are thus connected via signal technology via the signal processing unit 10. During operation, the (electrical) signal provided by the signal processing unit 10 is converted into sound waves by the receiver 12 as an electromechanical sound converter. The sound waves are guided into a sound hose 14, one end of which is fixed to the housing 4. The other end of the sound hose 14 is surrounded by a dome 16, which in the normal state is arranged in the ear canal 18 of the user of the hearing device 2, i.e. the wearer of the hearing device 2.

[0053] A basilar membrane 20 with a plurality of regions 22 is located in the ear canal 18 of the user. Each of these regions 22 is associated with a hair cell, so-called outer hair cell, not shown in detail. When a sound wave enters the ear canal 18, the sound wave causes the hair cell to vibrate, wherein the maximum amplitude of the vibration is formed in the region 22 associated with the frequency of the sound wave. Here, the amplitude of the vibration formed is also related to the amplitude of the sound wave. If the sound wave has only a single frequency, a maximum is formed only in one of the regions 22. On the other hand, if the sound wave has another frequency, a maximum is formed in another of the regions 22. When the amplitude is greater than the correspondingly associated hearing threshold, the nerves associated with the corresponding region 22 are stimulated, so that the user perceives the sound wave. Otherwise, the sound wave is not perceived.

[0054] In the case of some hair cell losses, the size of the achievable maximum value of the amplitude of the vibration is reduced, so that the corresponding nerve cells are stimulated only at relatively large amplitudes of the corresponding sound waves. Due to the reduction in number, the interaction between the hair cells also changes, so that the maximum is formed not only in the area associated with the corresponding frequency, but also in the surrounding area 22. Therefore, the user does not only perceive 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 help to ensure good frequency selectivity, it is their loss that leads to a wider excitation of the basilar membrane 20. Hearing loss is most often associated with outer hair cells. Since the outer hair cells have an active amplification mechanism, a nonlinear behavior of the basilar membrane excitation is thus generated. If the inner hair cells are still present, the processing in the inner ear in these areas is more linear.

[0055] The signal processing unit 10 is powered by a battery 24 arranged in the housing 4. The signal processing unit 10 conducts part of the electrical energy to the microphone 6 and the receiver 12. In this case, the signal processing unit 10 is at least partially executed in Figure 22 for operating a hearing device 2. In other words, the hearing device 2 is operated according to the method 26. In a first working step 28, an input signal 30 is provided. In this case, the input signal 30 is generated, for example, by means of a microphone 6 and is fed to the signal processing unit 10, so that the input signal 30 is received by means of the signal processing unit 10.

[0056] In a subsequent second working step 32, the input signal 30 is subjected to a frequency analysis, for which purpose a filter bank 34 of a signal processor of the signal processing unit 10 is used. In this process, the individual frequencies of the input signal 30 and the associated amplitudes are determined, thereby generating a spectrum. In addition, the individual components of the spectrum are classified.

[0057] exist Figure 3 , an example of a corresponding frequency spectrum of an input signal 30 is shown. The input signal 30 has two signal components 36, which are present due to useful noise, i.e., for example, due to speech in the sound picked up by means of the microphone 6. In addition, the input signal 30 has a remaining component 38, which in the example shown is also produced due to speech present in the sound picked up by means of the microphone 6.

[0058] The two signal components 36 each have a specific frequency 40, i.e., a frequency band, wherein the two specific frequencies 40 associated with different signal components 36 are different. In the region 22 of the basilar membrane 20 associated with the two specific frequencies 40, there is a reduction in the user's hair cells, which causes hearing loss in the user. Here, the reduction in one of the two regions 22 is greater than the reduction in the other of the two regions 22. In contrast, the frequency of the remaining component 38 corresponds to the following region in the region 22 of the basilar membrane 20, in which there is no reduction in hair cells or only a small reduction in hair cells. Therefore, the user's hearing is not limited at this frequency.

[0059] Two signal components 36 are selected. In other words, the signal components 36 are selected depending on the hearing loss of the user, whereas the remaining components 38 are not selected because there is no hearing loss at the associated frequencies. In summary, a plurality of, i.e. two, signal components 36 with the corresponding specific frequencies 40 are thus selected and are accordingly components of the input signal 30.

[0060] In the third working step 42, for each of the selected signal components 36, two additional signals 44 are respectively generated in a synthetic manner and thus provided. Each of these additional signals 44 has an additional specific frequency 46. In summary, a plurality of, i.e., four additional signals 44 are provided, wherein two of these additional signals 44 are respectively associated with one of the two signal components 36. Here, the additional specific frequency 46 of the corresponding additional signal 44 is different from the specific frequency 40 of the corresponding associated signal component 36, wherein the deviation between the specific frequency 40 and the two additional specific frequencies 46 is adjusted according to a parameter. In the example shown, the number of the remaining components 38 is used as a parameter, or, for example, the presence of the ambient volume and / or background noise is used as a parameter. The corresponding deviation can also be determined according to the hearing loss of the user.

[0061] In the example shown, the additional specific frequency 46 is directly connected to the specific frequency 40 of an associated signal component 36, so that the frequency band of the signal component 36 is framed by the frequency band of the associated additional signal 44, and these frequency bands are directly connected to each other. Therefore, one of the additional specific frequencies 46 is greater than the associated specific frequency 40, and another of the additional specific frequencies 46 is less than the associated specific frequency 40.

[0062] In the other signal component 36, the frequency band of one of the other signals 44 is directly connected. In contrast, the frequency band of another of the other signals 44 is slightly spaced apart from the frequency band of the associated signal component 36.

[0063] Furthermore, in a third working step 42, the amplitudes of the two signal components 36 are adjusted depending on the hearing loss of the user. In the example shown, the amplitudes of the signal components 36 of the input signal 30 are substantially equally large. Due to the adjustment according to the hearing loss of the user, in the example shown, after the adjustment, one of the two signal components 36 has a larger amplitude, wherein both amplitudes are increased.

[0064] In the subsequent fourth working step 48, the adjusted signal component 36, the further signal 44 and the remaining component 38 are combined into an output signal 50, so that the output signal 50 is generated according to the adjusted signal component 36 and the further signal 44. Therefore, the output signal 50 has Figure 4 The spectrum shown in .

[0065] In a subsequent fifth working step 52, the output signal 50 is directed to the earpiece 12, by means of which the sound is output into the auditory canal, which sound is directed into the auditory canal 18 due to the arrangement of the hearing device 2 during normal use. The output signal 50 is thus output by means of the earpiece 12, so that the sound is generated. In this case, in particular, the output signal 50 is first converted into an analog signal, so that an analog output signal 50 is output. In this case, the sound consists of different sound waves and corresponds to the (adjusted) signal component 36 and the further signal 44. In addition, in a variant not shown in detail, the output signal 50 is amplified by means of an amplifier.

[0066] The sound reaches the basilar membrane 20 of the user, thereby exciting the region 22. In this case, the further signal 44 is generated, so that a first time interval 54 and a second time interval 56 are formed. For this purpose, the further specific frequency 46 and the phase and amplitude of the further signal 44 are selected accordingly. The first time interval 54 alternates with the second time interval 56. During the first time interval 54, due to the interference of the sound waves corresponding to the further signal 44 with the sound waves corresponding to the signal component 36, the hair cells of the region 22 associated with the specific frequency 40 of the signal component 36 are excited. In contrast, during the second time interval 56, the hair cells associated with the same region 22 are not excited.

[0067] exist Figure 5 In order to explain the principle, two sound waves 58 are shown, which have different frequencies from each other. Here, in order to simplify the illustration, the amplitudes of the two sound waves 58 are selected to be equally large.

[0068] exist Figure 6 5 shows the superposition of two sound waves 58, i.e. the generated sound 60. Due to the interference, a first time interval 54 is generated, during which the contribution of the generated sound 60 is greater than the hearing threshold 62. In this case, the vibration of the hair cells is large enough to stimulate the associated nerves. In other words, the hair cells are excited. In contrast, when the generated sound 60 is less than the hearing threshold 62, no excitation is performed, and one of the second time intervals 56 is formed. Due to the alternating excitation of the associated hair cells, the sound can be perceived relatively accurately by the user.

[0069] Here, the additional signal 44 is designed to excite the hair cells of the area 22 associated with the corresponding associated specific frequency 40, but not to excite the adjacent area 22. Therefore, for the user, the specific frequency 40 can be relatively accurately perceived, and therefore the signal component 36 can be perceived and associated with the specific frequency 40. Therefore, although there is a loss of hair cells, the spectral resolution when the user listens is improved.

[0070] The signal component 36 is selected in dependence on the hearing loss of the user. In other words, the specific frequency 40 is associated with the region 22 in which the hair cell loss is present. However, when the corresponding signal component 36 is classified as belonging to the interference noise in the second working step 32, no associated further signal 44 is generated. Therefore, for the user, the interference noise is not perceived in an amplified manner either, so that the comfort level is increased.

[0071] The present invention is not limited to the embodiments described above. On the contrary, those skilled in the art can also derive other variations of the present invention without departing from the subject matter of the present invention. In addition, in particular, all individual features described in conjunction with the embodiments can also be combined with each other in other ways without departing from the subject matter of the present invention.

[0072] Reference numerals list

[0073] 2 Hearing devices

[0074] 4 Housing

[0075] 6 Microphones

[0076] 8 microphone units

[0077] 10 Signal Processing Unit

[0078] 12 Receiver

[0079] 14 Sound Hose

[0080] 16 Dome

[0081] 18 Ear canal

[0082] 20 Basement membrane

[0083] 22 Regions

[0084] 24 Batteries

[0085] 26 Methods

[0086] 28 First working step

[0087] 30 Input signal

[0088] 32 Second working step

[0089] 34 Filter Banks

[0090] 36 signal components

[0091] 38 remaining ingredients

[0092] 40 Specific frequency

[0093] 42 Third working step

[0094] 44 Another signal

[0095] 46 Additional specific frequencies

[0096] 48 Fourth working step

[0097] 50 Output signal

[0098] 52 Fifth working step

[0099] 54 First time interval

[0100] 56 Second time interval

[0101] 58 Soundwave

[0102] 60 Sounds generated

[0103] 62 Hearing Threshold

Claims

1. A method (26) for operating a hearing device (2), the hearing device comprising a microphone (6) and a receiver (12), the microphone and the receiver being connected via signal technology by means of a signal processing unit (10), wherein: - providing an input signal (30), - selecting a signal component (36) of the input signal (30) having a specific frequency (40), - providing a further signal (44) having a further specific frequency (46), - generating an output signal (50) as a function of the signal component (36) and the further signal (44), and - outputting the output signal (50) by means of the earpiece (12), thereby generating sound, wherein: The further signal (44) is designed to generate a first time interval (54) and a second time interval (56), wherein during the first time interval (54), hair cells associated in an area (22) of the user's basilar membrane (20) associated with the specific frequency (40) are excited due to interference, and wherein during the second time interval (56), the hair cells are not excited.

2. The method (26) according to claim 1, It is characterized in that The signal components (36) are selected based on the hearing loss of the user.

3. The method (26) according to claim 1 or 2, It is characterized in that A plurality of signal components are selected (36).

4. The method (26) according to any one of claims 1 to 3, It is characterized in that The further signal (44) is generated synthetically.

5. The method (26) according to any one of claims 1 to 4, It is characterized in that A plurality of further signals (44) are provided.

6. The method (26) according to any one of claims 1 to 5, It is characterized in that The amplitude of the signal component (36) is adjusted according to the hearing loss of the user.

7. The method (26) according to any one of claims 1 to 6, It is characterized in that The deviation between the specific frequency (40) and the other specific frequency (46) is adjusted according to a parameter.

8. The method (26) according to any one of claims 1 to 7, It is characterized in that If the signal component (36) is classified as belonging to interfering noise, the further signal (44) is not provided.

9. A hearing device (2), comprising a microphone (6) and an earpiece (12), the microphone and the earpiece being connected via signal technology by means of a signal processing unit (10), and the hearing device being operated according to the method (26) according to any one of claims 1 to 8.

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