Hearing aid with soft vent

Abstract

The present application discloses a hearing aid with a soft vent, where the hearing aid comprises: an input unit configured to receive an audible sound and to convert the audible sound into an electronic signal representative of the audible sound; a processing unit configured to receive the electronic signal, where the processing unit is configured to process the electronic signal in a first path to produce a first auditory sound and to process the electronic signal in a second path to produce a second auditory sound, the second path having a lower latency than the first path; an in-ear element having an output unit, wherein the output unit is configured to output a first auditory sound and a second auditory sound; a physical vent extends through the in-ear element to provide fluid communication between the first side of the in-ear element and the second side of the in-ear element to provide direct auditory sound.

Description

Technical Field

[0001] The present invention relates to the field of hearing aids. In particular, a hearing aid having a soft vent to supplement a traditional physical vent is disclosed herein. Background Art

[0002] In some cases, it is advantageous for a hearing aid user to perceive open sound (open perception) in frequency regions where amplification is not necessary. The problem is that to perceive open sound, a transparent sound path is required for all audible sounds. For the user, a limited audible sound bandwidth will reduce the perception of transparent open sound. For the user, delayed sound will also reduce the perception of transparent open sound.

[0003] If possible, large physical vents should be used. Large physical vents will not provide limited sound bandwidth. However, due to beneficial hearing instrument features such as noise reduction, transient protection, directionality, and hearing loss compensation at low and mid frequencies, large physical vents are not possible.

[0004] In addition, sound delay occurs due to the sound latency or group delay introduced by the domain switching signal processing in the standard processing path (e.g., the first path). Specifically, latency is introduced due to the processing from the time domain to the filter frequency domain and back to the time domain. Summary of the invention

[0005] Hearing aids

[0006] In one aspect of the present application, a hearing aid is provided. The hearing aid includes an input unit. The input unit is configured to receive an audible sound. The input unit may be configured to convert the audible sound into an electronic signal representing the audible sound. The hearing aid includes a processing unit. The processing unit is configured to receive an electronic signal. The processing unit is configured to process the electronic signal in a first path to produce a first audible sound. The processing unit is configured to process the electronic signal in a second path to produce a second audible sound. The second path has a lower latency than the first path. The hearing aid includes an in-ear element. The in-ear element has an output unit. The output unit is configured to output the first audible sound and the second audible sound. The hearing aid includes a physical vent. The physical vent may extend through the in-ear element to provide fluid communication between a first side of the in-ear element and a second side of the in-ear element to provide direct audible sound.

[0007] Disclosed herein are hearing aid embodiments having soft vents (i.e., software vents) (e.g., digital vents, electronic vents). Soft vents can supplement traditional (e.g., physical) vents. In some embodiments, soft vents can replace traditional vents. Soft vents (also referred to herein as second pathways) can be understood as parallel pathways for sound to pass through the hearing aid, outside of the normal (e.g., existing, first pathway) processing pathway. Soft vents can have low latency (e.g., low delay) compared to the normal processing pathway. For example, soft vents can have low latency by using simple signal processing. This low latency can provide an open sound to the user and achieve a low comb filtering effect. In some implementations, the soft vents are controllable, thereby providing flexibility for use in the hearing aid.

[0008] For soft vents (supplementary vents, second paths), short latency times can be achieved. When using small physical vents, the hearing aid has more responsibility to make the audible frequencies transparent to the initial sound picked up by the microphone and to perceive the open sound with as few artifacts as possible to the hearing aid user while providing good sound quality.

[0009] Thus, an improved hearing aid may be provided. Advantageously, compared to typical physical vents, soft vents will not succumb to sound leakage outside the ear canal, especially low frequency sounds. In addition, certain hearing aid examples may implement features such as noise reduction, directionality, transient noise reduction, etc. to change or switch soft vents when necessary to increase the effect of the feature. In addition, soft vents may enable streaming bass performance. In certain embodiments, the combination of a physical vent and a low latency processing path may be viewed as a combined system having the performance of a large physical vent without the disadvantages associated with using a hearing instrument for hearing loss compensation.

[0010] Additionally, advantageously, the hearing aid can deliver sound with low latency in the mid to high frequency region while conforming to low frequency amplification. Thus, certain hearing aid examples can address hearing loss issues such as reverse slope and cookie bite.

[0011] Furthermore, due to the low latency of the soft vent, such a hearing aid can provide sound with less comb filtering effects than with a normal vent. This will be even further improved due to appropriate amplification in the selected frequency region.

[0012] Additionally, through the optional use of a separate A / D converter with a higher sampling frequency, it is possible to add sounds at higher frequencies than would normally be processed.

[0013] In users with a sloped hearing loss, it is desirable to have a fairly large vent, since such users have normal to mild hearing loss in the low frequencies. This provides a sense of openness in the frequency region where amplification is not required. However, having a large open vent has several limitations:

[0014] - Low frequency sounds will leak out when streamed to the hearing aids, resulting in a very "tinny" sound;

[0015] - Hearing aid features such as noise reduction, directionality, transient protection, etc. have limited effect because direct sound through the vent is not processed by the feature;

[0016] - Traditional vents are only effective in low frequencies, but hearing loss types such as reverse slope and biscuit bite require good low frequency amplification because the user has normal to mild hearing loss in the low frequencies and requires a more open sound in the mid to high frequencies;

[0017] - Due to the delay in the hearing aid, there is a comb filtering effect when the processed sound is mixed with the direct sound from the vent, which produces a coloration of the sound.

[0018] The hearing aid disclosed herein may alleviate one or more of the problems discussed above and assist users with sloping hearing losses.

[0019] The hearing aid disclosed herein comprises an input unit configured to receive an audible sound, such as noise. The hearing aid may comprise an input unit for providing an electrical input signal representing the sound. The input unit may comprise an input transducer, such as a microphone, for converting the input sound into the electrical input signal. The input unit may comprise a wireless receiver for receiving a wireless signal comprising or representing the sound and providing the electrical input signal representing the sound.

[0020] The hearing aid disclosed herein includes a processing unit (e.g., a signal processor, a processor, a digital signal processor (DSP)). The processing unit is configured to receive an electronic signal and apply one or more processes (e.g., an element of the processing unit may modify the electronic signal). The processing unit may include a plurality of elements configured to modify the electronic signal.

[0021] The hearing aid may be adapted to provide frequency dependent gain and / or level dependent compression and / or frequency transposition of one or more frequency ranges to one or more other frequency ranges (with or without frequency compression) to compensate for a hearing impairment of a user. The compensation is performed in the first path. In one or more example hearing aids, the first path is configured to compensate for a hearing impairment of a hearing aid user.

[0022] The processing unit is configured to process the electronic signal in a first path (e.g., a first sound path) to produce a first auditory sound. The processing unit is configured to process the electronic signal in a second path (e.g., a second sound path) to produce a second auditory sound. In other words, the processing unit includes two parallel paths for processing the electronic signal.

[0023] As discussed herein, pathways (e.g., a first pathway and a second pathway) may be considered electronic processing pathways. For example, the first pathway and the second pathway may include processing elements that may apply one or more effects to an electronic signal. The electronic signal after passing through the first pathway may be considered a first processed signal. The electronic signal after passing through the second pathway may be considered a second processed signal. The first processed signal may be converted into a first audible sound. The second processed signal may be converted into a second audible sound.

[0024] In other words, the processing unit enables the electronic signal to be processed in two different paths. The first path and the second path may be considered as parallel paths.

[0025] In one or more example hearing aids, the same electronic signal may originate in each of the first and second pathways. The first and second pathways may modify the electronic signal in different ways. In one or more example hearing aids, the first pathway may include more processing elements than the second pathway. The second pathway may be a "simpler" pathway than the first pathway.

[0026] For example, the first path can be a fully digital hearing aid with a front-end chip and a main chip. The first path can be generally configured to compensate for hearing loss and / or hearing impairment. The first path is configured to overcome the hearing loss of the hearing aid user. For example, the main task of the first path is to provide the user with just the right audibility. The first path may include an amplifier for amplification. In addition, the first path may include a compressor, because the hearing loss is not linear, the compressor may apply appropriate compression. In addition, the first path may include a noise reduction system, a directional system, etc. to make the electronic signal pure. The first path may include using a filter bank to convert the domain of the electronic signal (for example, from the time domain to the frequency domain, and then back to the time domain). The use of a filter bank may result in higher latency.

[0027] As an example, the first path may include a front end with an analog-to-digital converter, input correction, filter bank analysis, noise reduction, audio-correction compression with a level estimator, filter bank synthesis, output correction, and a back end digital-to-analog converter. The analog-to-digital converter may operate at a higher sampling rate than the digital-to-analog converter.

[0028] In some implementations, the first and second paths may share the same input analog-to-digital converter, which is then downsampled to different sample rates when performing signal processing. The hearing aid may have separate digital-to-analog converters in the latter paths (one for the first path and one for the second path).

[0029] In its simplest form, the second path may have no components. In some implementations, the second path may have a simple filter such as a low pass filter, which may be formed with very few components. The second path may include a band pass filter (e.g., a high pass filter and a low pass filter). Alternatively, the second path may include an on / off switch. The switch may be configured to open and close the second path.

[0030] In one or more example hearing aids, the second path can be enabled to remain in the time domain, as opposed to converting to the frequency domain and then back to the time domain in the first path. This can significantly reduce the latency of the second path. In some embodiments, the second path does not convert the domain of the electronic signal. For example, the second path does not include a filter bank.

[0031] In one or more example hearing aids, the first pathway is configured to convert the electronic signal from the time domain to the frequency domain and then back to the time domain. In one or more example hearing aids, the second pathway maintains the electronic signal in the time domain.

[0032] The second passage may be referred to as a soft vent (eg, a digital vent or an electronic vent). The soft vent may be configured to mimic a real acoustic (eg, physical) vent.

[0033] Advantageously, the second path may have a lower latency than the first path. The second path may have a delay less than the first path. This may be caused by less processing applied in the second path than in the first path. For example, the first path may change the domain from the time domain to the time-filter bank domain and then change back to the time domain, which requires processing power. The second path may remain in the time domain, thereby reducing delays.

[0034] The hearing aid may further include an in-ear element. The in-ear element may be configured to be partially and / or completely inserted into the user's ear canal. The in-ear element may include an output unit. The output unit may be configured to output the first auditory sound and the second auditory sound.

[0035] In other words, the hearing aid may include an output unit for providing a stimulus perceived by the user as an acoustic signal (e.g., a first auditory sound and a second auditory sound) based on the processed electrical signal. The output unit may output a mixed signal based on the first auditory sound and the second auditory sound. The output unit may include a plurality of electrodes of a cochlear implant (of a CI-type hearing aid) or may include a vibrator of a bone conduction hearing aid. The output unit may include an output transducer. The output transducer may include a receiver (speaker) for providing the stimulus as an acoustic signal to the user (e.g., in an acoustic (air-conduction-based) hearing aid). The output transducer may include a vibrator for providing the stimulus as a mechanical vibration of the skull to the user (e.g., in a bone-attached or bone-anchored hearing aid). The output unit may (in addition or as an alternative) include a (e.g., wireless) transmitter for transmitting the sound picked up by the hearing aid (e.g., via a network, e.g., in a telephone operating mode, or in a headset configuration) to another device, such as a remote communication partner.

[0036] The hearing aid also includes a physical vent (e.g., an acoustic vent). The physical vent may be understood as a third passage (e.g., a third audio passage). The physical vent extends through the in-ear element to provide fluid communication between a first side of the in-ear element and a second side of the in-ear element. The first side of the in-ear element may generally be opposite to the second side of the in-ear element.

[0037] A physical vent may allow direct auditory sound (eg, not processed by a hearing aid) to pass through the in-ear element. The physical vent may be, for example, a lumen, a passageway, etc. Direct auditory sound may be audible sound.

[0038] Physical vents allow for an air ventilation effect, which can relieve pressure and / or moisture.

[0039] Typically, the use of physical vents can cause some problems for the user because there is a slight delay between the audio received from the physical vent and the audio received from a standard hearing aid, which causes a comb filter effect to the user. However, by using the second path disclosed herein, the comb filter effect can be reduced and / or eliminated. In addition, the use of the second path can achieve a more "open" feeling to the user due to the lower latency of the second path.

[0040] In one or more example hearing aids, the hearing aid may include three different sound paths. The first path is a sound path through the hearing aid for hearing loss compensation and noise reduction. The second path is a sound path through a soft vent. The second path can be used as a controlled bandpass filter with adjustable sound path gain. The third path is through a physical vent for dehumidification and pressure relief. The physical vent can behave as a low-pass filter with characteristics that depend on the size of the hole. The second sound path and the third sound path can together produce a perceived open sound to the user. The first sound path is used to compensate for hearing loss.

[0041] The first and second paths may share information to reduce audible comb filtering effects that occur when two equal signals mix and interfere.

[0042] The second sound path may have a less complex signal processing path to reduce latency, and the frequency bandwidth may be extended for this sound path compared to the first sound path when the hearing aid amplifier supports multiple sound path sample rates or supports an analog sound path.

[0043] The second sound path may have a controllable gain and a controllable cutoff frequency configured by the control logic of the signal processing running on the second path itself or by the control logic of the signal processing running on the first sound path.

[0044] As mentioned above, the second path may have a lower latency than the first path. In one or more example hearing aids, the second path has a latency of 0.3-0.5 ms. In one or more example hearing aids, the second path has a latency of 0.2-0.6 ms. In one or more example hearing aids, the first path has a latency of 9 ms. The latency may vary depending on the processing performed on the electronic signal in the first path and / or the second path. For example, the latency of the first path may be 1, 2, 3, 4, 5, 6, 7, 8, 9, or 10 ms.

[0045] In one or more example hearing aids, the second path may have a latency less than 10% of the latency of the first path. In one or more example hearing aids, the second path may have a latency less than 5% of the latency of the first path.

[0046] In one or more example hearing aids, the second path may have a latency similar to that of the physical vent. This may provide a better match between the second path and the physical vent, thereby reducing comb filtering effects. Having low latency in the second path may provide an open sound with low comb filtering effects.

[0047] The waiting time for a physical vent is essentially 0. It is only the speed of sound that determines the waiting time for a physical vent.

[0048] In one or more example hearing aids, the second path includes a filter configured to control the frequency shape of the electronic signal. A simple filter can be used to keep latency low. It would be advantageous if the filter could be configured and controlled during fitting and use. The control portion could be, for example, fitting software that features the hearing aid.

[0049] The filter may be a bandpass filter (e.g., high pass and low pass). The second path may be used as a bandpass filter. This may allow the second path to be complementary to a small physical vent. For example, the second path will operate at a higher frequency than the small physical vent, with a matched crossover frequency between the physical vent and the second path. The small physical vent in combination with the second path may be configured to mimic a larger physical vent.

[0050] The second path may include a separate analog-to-digital converter. For example, a separate analog-to-digital converter may be used in situations where the frequencies are above the normal cut-off frequency of the hearing aid.

[0051] In one or more example hearing aids, the hearing aid may include a control unit. The control unit may be configured to control one or more aspects of the second pathway. The control unit may be configured to generate a control signal for operation of the second pathway.

[0052] In one or more example hearing aids, the hearing aid further comprises a control unit configured to open or close the second path. For example, the control unit may be configured to generate a control signal indicating opening or closing the second path. The second path may include an on / off switch, and the control signal may indicate whether the on / off switch is closed or open. The control unit may be configured to generate a control signal indicating a change in the second path (e.g., from off to on, or vice versa).

[0053] There may be some situations where it is not necessary to use the second path. For example, during hearing aid streaming, it may be useful for the user to have the second path off. Thus, it may be beneficial to turn off the second path, thereby saving energy in the hearing aid.

[0054] In one or more exemplary hearing aids, the hearing aid further comprises a control unit configured to modify the second path based on the electronic signal and / or the feedback signal. In other words, the control unit can implement real-time changes of the second path according to the sound environment.

[0055] For example, modifying the second path may include applying bandpass filtering with a selectable cut-off frequency and level gain variation. Modifying the second path may include changing the cut-off frequency and / or the level gain variation.

[0056] In some embodiments, modifying the second path may include complex filtering to reduce comb filtering effects. Modifying the second path may be based on the acoustics prescribed by the audiologist to simulate the real acoustics of a larger vent. The bandpass filter of the second path may complement the physically prescribed vent size. This means that the cutoff frequency and / or shape from the bandpass filter may be modified in the second path to extend the shape of the physical vent. When it comes to noise reduction, modifying the second path may include adjusting the level of the second path and / or the frequency range of the bandpass filter. Information about the specific type of hearing loss can also be used to shape the overall frequency response of the second sound path by modifying the second path.

[0057] For example, when streaming through a hearing aid, modifying the second path may include closing the second path to provide better bass. In embodiments where the feedback system detects howling, modifying the second path may include closing and / or attenuating and / or applying a notch filter in the frequency region where the howling is detected.

[0058] In a noisy environment, modifying the second path may include closing and / or attenuating the second path to improve the conditions of the noise reduction system and the directional system.

[0059] When a transient is detected by the transient noise reduction system of the hearing aid, modifying the second path may include closing the second path to increase the likelihood of attenuating the transient.

[0060] The feedback signal may be a signal received by the hearing aid indicating that the user will receive feedback. Reducing the feedback indicated by the feedback signal would be beneficial. Thus, if there is high feedback, as indicated by the feedback signal, the control unit may modify the second path to reduce said feedback.

[0061] For example, the second path may include a controllable filter. The controllable filter may be configured to modify the electronic signal to control the shape of the second auditory sound. The control unit may be configured to generate a control signal indicating the specific filtering to be applied by the controllable filter.

[0062] In one or more example hearing aids, the soft vent is equivalent to a physical vent of 0.88 mm diameter and 19 mm length. In other words, the soft vent functions as an equivalent to a physical vent of a specific size. The size equivalence relationship may vary.

[0063] For applications where sound is streamed to hearing aids, it is beneficial for the hearing aids to perceive the best possible sound quality by being transparent to the content of the initial stream. With large physical vents, it is difficult to reproduce low and mid-frequency content due to limited speaker sound intensity and leakage through the physical vents. Therefore, small physical vents are beneficial.

[0064] In one or more example hearing aids, the second path does not include a filter bank, a noise reduction system, and a hearing loss compensation system. For example, the first path may include a filter bank, a noise reduction system, and a hearing loss compensation system. This enables the second path to have a much lower latency than the first path.

[0065] In one or more example hearing aids, the second path includes only a high pass filter for modifying the electronic signal. The high pass filter may be a biquad filter. The high pass filter may be updated by a control logic unit storing different filter coefficients to simulate different acoustic vents.

[0066] In one or more example hearing aids, the processing unit is configured to mix the first auditory sound and the second auditory sound to generate an output sound, wherein the output unit is configured to output the output sound.

[0067] For example, the output unit may output two different sounds, namely a first auditory sound and a second auditory sound. Alternatively or in combination, the output unit may output a single sound (e.g., an output sound) that is a mixture of the first auditory sound and the second auditory sound. The processor may include a mixer configured to mix the first auditory sound and the second auditory sound.

[0068] In one or more example hearing aids, the electronic signal is at least partially a digital signal. In one or more example hearing aids, the electronic signal is at least partially an analog signal. In one or more example hearing aids, the electronic signal is at least partially a digital signal and at least partially an analog signal. In one or more example hearing aids, the electronic signal is completely a digital signal.

[0069] In one or more example hearing aids, the second path is configured to produce a second auditory sound at a frequency of 9.5 KHz and higher. In one or more example hearing aids, the second path is configured to produce an auditory sound at a frequency of 9.10-15 KHz. For example, the second path may include an A / D converter separate from the first path. The A / D converter may have a high sampling frequency, such as a sampling frequency of 32 KHz. This enables the second path to achieve higher frequencies. For analog solutions, even higher frequencies can be used.

[0070] In other words, if the hearing aid has a nearly closed physical vent, it will act as a low pass filter and not let natural high frequency sounds through. Currently, the first path is limited to a sample rate of 20,000 Hz (in practice, up to 9.5 KHz frequency bandwidth), so the first path will limit the experience (hearing). The second path can have a higher sample rate than the first path, passing frequencies higher than 9.5 KHz (more transparent to hearing at higher frequencies).

[0071] In one or more example hearing aids, a notch filter may be used. For example, a notch filter may be in a first path. A notch filter may be in a second path. A notch filter may be in a first path and a second path. If the hearing aid detects a howling or a howling tendency and determines the frequency at which the howling occurs, a notch filter at that frequency may improve feedback performance.

[0072] In the second path, this can also be achieved with parallel biquad filters. In the first path, this can be achieved in the time-filter bank domain using other types of signal processing such as envelope processing. Dynamic filters, controllable filters, real-time control can be non-static filter designs. In practice, "dynamics, etc." is updating the filter coefficients of the biquad filter. Controlling the second path from other logic in the first signal path such as feedback, noise reduction, transient noise reduction, audio correction features means changing the second biquad filter coefficients or signal amplitudes (such as muting the second path) in real time (every first signal path frame).

[0073] The hearing aid may consist of or form part of a portable (i.e. configured to be wearable) device, such as a device comprising a local energy source such as a battery, such as a rechargeable battery. The hearing aid may for example be a low weight, easily wearable device, such as having a total weight of less than 100g, such as less than 20g, such as less than 5g.

[0074] The hearing aid may comprise a "forward" (or "signal") path between an input and an output of the hearing aid (e.g. between an input unit and an output unit) for processing audio signals. A processing unit (e.g. a signal processor) may be located in the forward path (e.g. along a first path and a second path). The signal processor may be adapted to provide a frequency-dependent gain according to the specific needs of the user (e.g. hearing loss). The hearing aid may comprise an "analysis" path having functional parts for analyzing signals and / or controlling processing of the forward path. Part or all of the signal processing in the analysis path and / or the forward path may be performed in the frequency domain, in which case the hearing aid comprises appropriate analysis and synthesis filter banks. Part or all of the signal processing in the analysis path and / or the forward path may be performed in the time domain.

[0075] The analog electrical signal representing the acoustic signal can be converted into a digital audio signal in an analog-to-digital (AD) conversion process, where the analog signal is sampled at a predetermined sampling frequency or sampling rate f. s Sampling, f s For example, in the range from 8 kHz to 48 kHz (adapted to the specific needs of the application) at discrete time points t n (or n) provides digital samples x n (or x[n]), each audio sample is passed through a predetermined N b The bit represents the sound signal at t n The value of N b For example, in the range from 1 to 48 bits, such as 24 bits. Each audio sample thus uses N b bit quantization (resulting in 2 Nb different possible values). A digital sample x has a 1 / f s The time length, such as 50μs, for f s= 20kHz. Multiple audio samples can be arranged in time frames. A time frame can include 64 or 128 audio data samples. Other frame lengths can be used depending on the actual application.

[0076] The hearing aid may include an analog-to-digital (AD) converter to digitize an analog input (e.g., from an input transducer such as a microphone) at a predetermined sampling rate, such as 20 kHz. The hearing aid may include a digital-to-analog (DA) converter to convert the digital signal into an analog output signal, such as for presentation to a user via an output transducer.

[0077] The hearing aid, such as the input unit and / or the antenna and transceiver circuitry, may comprise a transform unit for transforming a time domain signal into a signal in a transform domain (e.g. frequency domain or Laplace domain, Z transform, wavelet transform, etc.). The transform unit may consist of or include a time-frequency (TF) transform unit for providing a time-frequency representation of the input signal. The time-frequency representation may comprise an array or mapping of corresponding complex or real values ​​of the signal concerned in a specific time and frequency range. The TF transform unit may comprise a filter bank for filtering the (time-varying) input signal and providing a plurality of (time-varying) output signals, each output signal comprising a distinct frequency range of the input signal. The TF transform unit may comprise a Fourier transform unit (e.g. a discrete Fourier transform (DFT) algorithm, a short-time Fourier transform (STFT) algorithm, or a similar algorithm) for transforming the time-varying input signal into a (time-varying) signal in the (time-)frequency domain. The minimum frequency f is taken into account by the hearing aid. min To the maximum frequency f max The frequency range of may include a portion of the typical human hearing range from 20 Hz to 20 kHz, for example a portion of the range from 20 Hz to 12 kHz. Typically, the sampling rate f s Greater than or equal to the maximum frequency f max twice, that is, f s ≥2f max The signals of the forward path and / or analysis path of the hearing aid may be split into NI frequency bands (e.g. of uniform width), wherein NI is, for example, greater than 5, such as greater than 10, such as greater than 50, such as greater than 100, such as greater than 500, at least parts of which are processed separately. The hearing aid may be adapted to process the signals of the forward and / or analysis path in NP different frequency channels (NP≤NI). The frequency channels may be of uniform or non-uniform width (e.g. the width increases with frequency), overlapping or non-overlapping.

[0078] The hearing aid may also include other appropriate functions for the application in question, such as compression, noise reduction, etc.

[0079] A hearing aid may comprise a hearing instrument, such as a hearing instrument adapted to be located at the ear of a user or to be located fully or partially in the ear canal, such as an earphone, a headset, an ear protection device or a combination thereof. A hearing system may comprise a loudspeaker amplifier (comprising a plurality of input transducers (such as a microphone array) and a plurality of output transducers such as one or more loudspeakers, and one or more audio (and possibly video) microphones, such as for use in an audio conferencing situation), such as comprising a beamformer filter unit, such as to provide a plurality of beamforming capabilities.

[0080] The above discussion also applies to headphones.

[0081] method

[0082] In one aspect, the present application also provides a method for operating a hearing aid. The method includes: receiving an audible sound through an input unit of the hearing aid. The method includes: converting the audible sound into an electronic signal representing the audible sound through the input unit. The method includes: generating a first audible sound through a first processing path based on the electronic signal through a processing unit. The method includes: generating a second audible sound through a second processing path based on the electronic signal through a processing unit, wherein the second processing path has a lower latency than the first processing path. The method includes: outputting the first audible sound and the second audible sound through an output unit of the hearing aid.

[0083] When appropriately replaced by corresponding procedures, some or all structural features of the hearing aid described above, described in detail in the "Detailed Description of the Invention" or defined in the claims may be combined with the implementation of the method of the present invention, and vice versa. The implementation of the method has the same advantages as the corresponding hearing aid.

[0084] Computer readable medium or data carrier

[0085] The present invention further provides a tangible computer-readable medium (data carrier) storing a computer program including program code (instructions), which, when executed on a data processing system (computer), enables the data processing system to execute (implement) at least part (such as most or all) of the steps of the method described above, described in detail in the "Specific Implementation Method" and defined in the claims.

[0086] As an example but not limitation, the aforementioned tangible computer readable medium may include RAM, ROM, EEPROM, CD-ROM or other optical disk storage, magnetic disk storage or other magnetic storage device, or any other medium that can be used to execute or store the desired program code in the form of instructions or data structures and can be accessed by a computer. As used herein, disks include compact disks (CDs), laser disks, optical disks, digital versatile disks (DVDs), floppy disks, and blue-ray disks, wherein these disks usually reproduce data magnetically, while these disks can reproduce data optically with lasers. Other storage media include storage in DNA (e.g., in synthetic DNA chains). Combinations of the above disks should also be included in the scope of computer readable media. In addition to being stored on tangible media, computer programs can also be transmitted via transmission media such as wired or wireless links or networks such as the Internet and loaded into a data processing system to run at a location different from the tangible media.

[0087] For example, a tangible computer-readable medium (data carrier) stores a computer program including program code (instructions), which causes a data processing system (computer) to perform (complete) at least part (e.g., most or all) of the following processing: receiving audible sounds through an input unit of a hearing aid; converting the audible sounds into electronic signals representing the audible sounds through the input unit; generating a first audible sound through a first processing path based on the electronic signals through a processing unit; generating a second audible sound through a second processing path based on the electronic signals through the processing unit, wherein the second processing path has a lower latency than the first processing path; and outputting the first audible sound and the second audible sound through an output unit of the hearing aid.

[0088] Computer Programs

[0089] In addition, the present application provides a computer program (product) comprising instructions, which, when executed by a computer, causes the computer to execute (the steps of) the method described above, described in detail in the “Detailed Description” and defined in the claims.

[0090] A computer program (product) comprising instructions, which, when executed by a computer, cause the computer to perform at least part of the following processing: receiving an audible sound through an input unit of a hearing aid; converting the audible sound into an electronic signal representing the audible sound through the input unit; generating a first audible sound through a first processing path based on the electronic signal through a processing unit; generating a second audible sound through a second processing path based on the electronic signal through the processing unit, wherein the second processing path has a lower latency than the first processing path; and outputting the first audible sound and the second audible sound through an output unit of the hearing aid.

[0091] Data processing system

[0092] On the one hand, the present invention further provides a data processing system comprising a processor and a program code, wherein the program code enables the processor to perform at least part (such as most or all) of the steps of the method described above, described in detail in the "Specific Implementation Method" and defined in the claims.

[0093] The data processing system includes a processor and a program code for causing the processor to perform at least part (e.g., most or all) of the following processing: receiving an audible sound through an input unit of a hearing aid; converting the audible sound into an electronic signal representing the audible sound through the input unit; generating a first audible sound through a first processing path based on the electronic signal through the processing unit; generating a second audible sound through a second processing path based on the electronic signal through the processing unit, wherein the second processing path has a lower latency than the first processing path; and outputting the first audible sound and the second audible sound through an output unit of the hearing aid.

[0094] definition

[0095] In this specification, a hearing aid, such as a hearing instrument, refers to a device suitable for improving, enhancing and / or protecting the hearing ability of a user by receiving an acoustic signal from the user's environment, generating a corresponding audio signal, possibly modifying the audio signal, and providing the possibly modified audio signal as an audible signal to at least one ear of the user. The audible signal may be provided, for example, in the form of an acoustic signal radiated into the user's outer ear, an acoustic signal transmitted to the user's inner ear as mechanical vibrations through the bone structure of the user's head and / or through parts of the middle ear, and an electrical signal transmitted directly or indirectly to the user's cochlear nerve.

[0096] The hearing aid may be configured to be worn in any known manner, such as as a unit worn behind the ear (with a tube directing the radiated acoustic signal into the ear canal or with an output transducer such as a loudspeaker arranged close to or in the ear canal), as a unit arranged wholly or partly in the auricle and / or ear canal, as a unit connected to a fixed structure implanted in the skull, such as a vibrator, or as a connectable or wholly or partly implanted unit, etc. The hearing aid may comprise a single unit or several units that communicate with each other (e.g. acoustically, electrically or optically). The loudspeaker may be arranged in a housing together with the other components of the hearing aid, or it may itself be an external unit (possibly in combination with a flexible guiding element such as a dome-shaped element).

[0097] The hearing aid may be adapted to the needs of a specific user, such as hearing loss. The configurable signal processing circuit of the hearing aid may be adapted to apply frequency- and level-dependent compression amplification of the input signal. The customized frequency- and level-dependent gain (amplification or compression) may be determined during the fitting process by the fitting system based on the user's hearing data, such as an audiogram, using the basic principles of fitting (e.g. adaptation to speech). The frequency- and level-dependent gain may, for example, be embodied in a processing parameter, uploaded to the hearing aid, for example, via an interface to a programming device (fitting system), and used by a processing algorithm executed by the configurable signal processing circuit of the hearing aid.

[0098] "Hearing system" refers to a system including one or two hearing aids. "Binaural hearing system" refers to a system including two hearing aids and adapted to provide audible signals to the two ears of a user in a coordinated manner. A hearing system or binaural hearing system may also include one or more "auxiliary devices" that communicate with the hearing aids and affect and / or benefit from the functions of the hearing aids. The aforementioned auxiliary devices may include at least one of the following: a remote controller, a remote microphone, an audio gateway device, an entertainment device such as a music player, a wireless communication device such as a mobile phone (e.g., a smart phone) or a tablet computer or another device, for example, including a graphical interface. Hearing aids, hearing systems or binaural hearing systems may be used, for example, to compensate for the loss of hearing ability of hearing-impaired persons, enhance or protect the hearing ability of normal hearing persons, and / or transmit electronic audio signals to people. Hearing aids or hearing systems may, for example, form part of or interact with a broadcasting system, an active ear protection system, a hands-free telephone system, a car audio system, an entertainment (e.g., television, music playback or karaoke) system, a teleconferencing system, a classroom amplification system, etc. BRIEF DESCRIPTION OF THE DRAWINGS

[0099] Various aspects of the present invention will be best understood from the detailed description below in conjunction with the accompanying drawings. For clarity, the drawings are schematic and simplified, and only the details necessary for understanding the present invention are given, while other details are omitted. Throughout the specification, the same reference numerals are used for the same or corresponding parts. The various features of each aspect may be combined with any or all features of the other aspects. These and other aspects, features and / or technical effects will be apparent from and illustrated in conjunction with the following figures, in which:

[0100] Figure 1 shows a schematic example of a hearing aid according to the invention;

[0101] Figure 2 shows a schematic example of a hearing aid according to the invention;

[0102] Figure 3 shows a schematic example of a hearing aid according to the invention;

[0103] Figure 4An example of a reverse slope hearing loss problem that can be alleviated by a hearing aid according to the present invention is shown;

[0104] Figure 5 An example of a cookie-cutter hearing loss problem that can be alleviated by a hearing aid according to the present invention is shown;

[0105] Figure 6 An example of a method of operation of a hearing aid according to the invention is shown.

[0106] By the detailed description given below, the further scope of application of the present invention will be apparent. However, it should be understood that while the detailed description and specific examples show the preferred embodiments of the present invention, they are only provided for illustrative purposes. For those skilled in the art, based on the following detailed description, other embodiments of the present invention will be apparent. DETAILED DESCRIPTION

[0107] The detailed description proposed below in conjunction with the accompanying drawings serves as a description of a variety of different configurations. The detailed description includes specific details for providing a thorough understanding of a number of different concepts. However, it is apparent to those skilled in the art that these concepts can be implemented without these specific details. Several aspects of the apparatus and method are described by a number of different blocks, functional units, modules, components, circuits, steps, processes, algorithms, etc. (collectively referred to as "elements"). Depending on the specific application, design limitations or other reasons, these elements can be implemented using electronic hardware, computer programs or any combination thereof.

[0108] The electronic hardware may include microelectromechanical systems (MEMS), (e.g., application specific) integrated circuits, microprocessors, microcontrollers, digital signal processors (DSPs), field programmable gate arrays (FPGAs), programmable logic devices (PLDs), gating logic, discrete hardware circuits, printed circuit boards (PCBs) (e.g., flexible PCBs), and other suitable hardware configured to perform a number of different functions described in this specification, such as sensors for sensing and / or recording physical properties of the environment, device, user, etc. Computer programs shall be broadly construed as instructions, instruction sets, codes, code segments, program codes, programs, subroutines, software modules, applications, software applications, software packages, routines, subroutines, objects, executables, execution threads, programs, functions, etc., whether referred to as software, firmware, middleware, microcode, hardware description language, or otherwise.

[0109] The present application relates to the field of hearing aids.

[0110] Figure 1An example of a hearing aid 100 according to the present invention is shown. The figure has been simplified for ease of understanding. As shown, the hearing aid comprises an input unit 102 configured to receive an audible sound 50. The input unit 102 converts the audible sound 50 into an electronic signal 104 representing the audible sound 50. The electronic signal 104 may be at least partially a digital signal and / or at least partially an analog signal. The electronic signal 104 may be a completely digital signal or may be a completely analog signal.

[0111] The hearing aid 100 further comprises a processing unit 106 configured to receive the electronic signal 104. The processing unit 106 is configured to apply one or more processes to the electronic signal 104 to provide improved audio to a user of the hearing aid 100. In other words, the processing unit 106 may comprise one or more elements that affect the electronic signal 104. These elements include, for example, filters, time filter banks, etc.

[0112] As shown, the processing unit 106 is configured to process the electronic signal 104 in a first path 110. The electronic signal 104 is processed in the first path 110 to generate a first audible sound 112. For example, the processing unit 106 may process the electronic signal 104 to generate a first processed signal 114, which may indicate the first audible sound 112.

[0113] Furthermore, the processing unit 106 is configured to process the electronic signal 104 in the second path 120. The electronic signal 104 is processed in the second path 120 to generate a second audible sound 122. For example, the processing unit 106 may process the electronic signal 104 to generate a second processed signal 124, which may indicate the second audible sound 122.

[0114] Advantageously, the second pathway 120 may have a lower latency than the first pathway 110. For example, the second pathway may have a latency of 0.3-0.5 ms, while the first pathway has a latency of 9 ms. The specific latency may vary depending on the processing elements used on the first pathway and the second pathway. The second pathway 120 may not include a filter bank, a noise reduction system, and / or a hearing loss compensation system, thereby enabling faster processing of the electronic signal 104. Optionally, the second pathway 120 may include a filter configured to control the frequency shape of the electronic signal 104. The second pathway may be configured to produce a second auditory sound 122 at frequencies of 9.5 KHz and higher.

[0115] The hearing aid 100 further comprises an in-ear element having an output unit 130. The output unit 130 is configured to output the first auditory sound 112 and the second auditory sound 122. Figure 1 As shown in FIG. 1 , the in-ear element is completely connected within the hearing aid 100. Alternatively, the in-ear element may be in a separate housing and electrically connected to the out-of-ear element (via Figure 1).

[0116] As shown, the output unit 130 can separately output the first auditory sound 112 and the second auditory sound 122. In some examples, the processing unit 106 is configured to mix the first auditory sound 112 and the second auditory sound 122 to generate an output sound, wherein the output unit 130 is configured to output the output sound. The processing unit 106 can mix the first electronic signal and the second electronic signal to generate the output sound.

[0117] Additionally, as shown, hearing aid 100 includes physical vent 132. Physical vent 132 may extend through the in-ear element to provide fluid communication between a first side 134 of the in-ear element and a second side 136 of the in-ear element to provide direct auditory sound 138. Direct auditory sound 138 may be audible sound 50.

[0118] Optionally, the hearing aid 100 may include a control unit 140. The control unit 140 may be configured to generate and / or transmit a control signal 142. As shown, the control unit 140 may provide the control signal 142 to the processing unit 106. The control unit 140 may be configured to open or close the second path 120. The control unit 140 may be configured to modify the second path 120 based on the electronic signal 104 and / or the feedback signal.

[0119] Figure 2 200 shows a schematic example of a hearing aid according to the present invention. Figure 1 The hearing aid 100 is more complicated. For convenience, it is not combined Figure 2 All aspects of the hearing aid 200 are shown or discussed.

[0120] As shown, the hearing aid 200 includes an input unit 202 configured to receive audible sounds and convert the audible sounds into electronic signals representing the audible sounds.

[0121] The hearing aid 200 comprises a processing unit 203. The processing unit 203 comprises a first path 212 and a second path 220.

[0122] As shown, the first path 212 may include a plurality of elements that improve the user's auditory experience, but also increase the latency. For example, the first path 212 may include an amplifier 204, a digital signal processor 206 including a filter bank, and a feedback controller 208. Other elements may also be included. The output unit 210 may output the first auditory sound from the first path 212.

[0123] like Figure 2As shown in , the second path 220 is substantially simpler than the first path 212. The second path 220 may include, for example, a filter or a switch 220. In addition, the electronic signal is passed to the output unit 210 to output the second auditory sound. This results in significantly lower latency than the first path 212.

[0124] The hearing aid also includes a physical vent 230 .

[0125] Figure 3 300 includes a hearing aid housing 314. The hearing aid 300 is configured to be worn behind the ear of a user and includes a behind-the-ear (BTE) portion 302 and an in-the-ear element 304. The behind-the-ear portion 302 is connected to the in-the-ear element 304 via a connector 306. However, the hearing aid 300 may be configured in other ways, such as as a completely in-the-ear hearing aid.

[0126] exist Figure 3 In an embodiment of the hearing aid of the invention, the behind-the-ear portion 302 comprises an input unit 310 comprising an input transducer (e.g. a microphone) for providing an electrical signal representative of audible sound. The input unit further comprises a wireless receiver (or transceiver) for providing directly received auxiliary audio and / or control input signals (and / or enabling transmission of audio and / or control signals to other devices such as another hearing device, or to a remote control or processing device or telephone).

[0127] The hearing aid 300 further comprises a processing unit 316, such as a configurable signal processor (DSP, e.g., a digital (audio) signal processor), e.g., comprising a processor for applying a frequency- and level-dependent gain, thereby, for example, providing hearing loss compensation, beamforming, noise reduction, filter bank functionality, and other digital functions of the hearing device. The processing unit 316 is configured to process electronic signals in the first path and the second path discussed herein.

[0128] The processing unit 316 is adapted to access the memory. The processing unit 316 is further configured to process one or more electrical input audio signals and / or one or more directly received auxiliary audio input signals based on a currently selected (enabled) hearing aid program / parameter setting (e.g., or automatically selected based on one or more sensors, or selected based on input from a user interface).

[0129] The hearing aid 300 further comprises an output unit 318 (e.g., an output transducer) that provides stimulation that can be perceived as sound by the user based on the processed audio signal from the processor or a signal derived therefrom. The output unit 318 can be located in the in-ear element 304, such as Figure 3 as shown in .

[0130] Hearing aid 300, and in particular in-ear element 304, may include physical vent 308 as discussed herein. As shown, physical vent 308 extends through in-ear element 304 to provide fluid communication between a first side of in-ear element 304 and a second side of in-ear element 304 to provide direct auditory sound.

[0131] Figure 4 An example of a reverse slope hearing loss problem which can be alleviated by a hearing aid according to the invention is shown.Although uncommon, reverse slope hearing loss is distressing to users with such a loss due to the lack of satisfactory treatment methods.

[0132] The hearing aid disclosed herein can help alleviate reverse slope hearing loss. With reverse slope hearing loss problems, gain is needed, and transparent open sound is desired at high frequencies. This is the opposite of what an open dome provides for normal slope hearing loss. The hearing aid disclosed herein can act as a reverse vent, achieving open sound while applying gain at the necessary frequencies.

[0133] For a "normal" grade hearing loss, the user wants amplification at high frequencies, but at low frequencies the user typically wants appropriate openness, hence the physical vent and this second pathway.

[0134] For reverse slope hearing loss, the opposite is true. The user wants amplification in the low frequencies, but openness in the high frequencies. The former can be achieved with a relatively closed fit such as a small vent. A closed fit does not provide a sense of openness in the high frequencies. This is achieved using a second channel.

[0135] Figure 5 An example of a cookie bite hearing loss problem that can be alleviated by a hearing aid according to the present invention is shown. Figure 4 The reverse slope discussed is of the same kind.Similarly, biscuit bite hearing losses, though uncommon, are vexing to pharmacists because of the lack of satisfactory treatment options in dealing with them.

[0136] The hearing aid disclosed herein can help alleviate the cookie bite problem. Due to cookie bite hearing loss, gain is needed and transparent open sound is desired in the mid and high frequencies. The hearing aid disclosed herein can provide such a solution.

[0137] For cookie bite, users have almost the same problem as with reverse slope hearing loss. Users also want an open feel in the high frequencies.

[0138] Figure 6An example of an operating method of a hearing aid according to the present invention is shown. The method 600 includes step 602, receiving an audible sound through an input unit of the hearing aid. The method 600 includes step 604, converting the audible sound into an electronic signal representing the audible sound through the input unit. The method 600 includes step 606, generating a first audible sound through a first processing path based on the electronic signal through a processing unit. The method 600 includes step 608, generating a second audible sound through a second processing path based on the electronic signal through a processing unit, wherein the second processing path has a lower latency than the first processing path. The method 600 includes step 610, outputting the first audible sound and the second audible sound through an output unit of the hearing aid.

[0139] The structural features of the apparatus described above, described in detail in the “Detailed Description of the Invention” and defined in the claims may be combined with the steps of the method of the present invention when appropriately replaced by corresponding processes.

[0140] Unless expressly stated, the singular forms "one", "the" used herein include the plural form (i.e., have the meaning of "at least one"). It should be further understood that the terms "having", "including" and / or "comprising" used in the specification indicate the presence of the described features, integers, steps, operations, elements and / or parts, but do not exclude the presence or addition of one or more other features, integers, steps, operations, elements, parts and / or combinations thereof. It should be understood that, unless expressly stated, when an element is referred to as being "connected" or "coupled" to another element, it may be directly connected or coupled to the other element, or there may be an intermediate intervening element. As used herein, the term "and / or" includes any and all combinations of one or more listed related items. Unless expressly stated, the steps of any method disclosed herein do not have to be performed in the exact order disclosed.

[0141] It should be appreciated that reference to "an embodiment" or "embodiment" or "aspect" or features that "may" include in this specification means that the specific features, structures or characteristics described in conjunction with the embodiment are included in at least one embodiment of the present invention. In addition, the specific features, structures or characteristics may be appropriately combined in one or more embodiments of the present invention. The foregoing description is provided to enable those skilled in the art to implement the various aspects described herein. Various modifications will be apparent to those skilled in the art.

[0142] The claims are not limited to the various aspects shown herein, but rather have the full scope consistent with the claim language wherein, unless expressly stated otherwise, elements referred to in the singular do not mean "one and only one" but rather "one or more." Unless expressly stated otherwise, the term "some" means one or more.

Claims

1. A hearing aid, comprising: an input unit configured to receive audible sound and convert the audible sound into an electronic signal representing the audible sound; a processing unit configured to receive the electronic signal, wherein the processing unit is configured to - processing the electronic signal in a first path to produce a first audible sound; and - processing the electronic signal in a second path to produce a second audible sound, the second path having a lower latency than the first path; an in-ear element having an output unit, wherein the output unit is configured to output a first auditory sound and a second auditory sound; A physical vent extends through the in-ear element to provide fluid communication between a first side of the in-ear element and a second side of the in-ear element to provide direct auditory sound.

2. The hearing aid according to claim 1, wherein: The second pass has a latency of 0.3-0.5 ms.

3. The hearing aid according to claim 1, wherein: The first pass has a latency of 9 ms.

4. The hearing aid according to claim 1, wherein: The second path includes a filter configured to control a frequency shape of the electronic signal.

5. The hearing aid according to claim 1, further comprising a control unit configured to open or close the second path.

6. The hearing aid according to claim 1, further comprising a control unit configured to modify the second path based on the electronic signal and / or the feedback signal.

7. The hearing aid according to claim 1, wherein: The second passage is equivalent to a physical vent with a diameter of 0.88 mm and a length of 19 mm.

8. The hearing aid according to claim 1, wherein: The second path does not include the filter bank, the noise reduction system and the hearing loss compensation system.

9. The hearing aid according to claim 1, wherein: The processing unit is configured to mix the first auditory sound and the second auditory sound to generate an output sound, wherein the output unit is configured to output the output sound.

10. The hearing aid according to claim 1, wherein: The electronic signal is at least partially a digital signal.

11. The hearing aid according to claim 1, wherein: The electronic signal is at least partially an analog signal.

12. The hearing aid according to claim 1, wherein: The second path is configured to produce second audible sounds at frequencies of 9.5 KHz and above.

13. The hearing aid according to claim 1, wherein: The first path is configured to convert the electronic signal from the time domain to the frequency domain and then back to the time domain, wherein the second path maintains the electronic signal in the time domain.

14. The hearing aid according to claim 1, wherein: The first pathway is configured to compensate for hearing impairment of a hearing aid user.

15. A method of operating a hearing aid, the method comprising: receiving audible sound through an input unit of the hearing aid; converting the audible sound into an electronic signal representing the audible sound via the input unit; generating, by the processing unit, a first auditory sound based on the electronic signal via a first processing path; generating, by the processing unit, a second auditory sound based on the electronic signal via a second processing path, wherein the second processing path has a lower latency than the first processing path; and Through the output unit of the hearing aid, the first auditory sound and the second auditory sound are output.

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