Patent Grant
9432783
The present invention relates to a method for fitting a hearing device. More specifically, the present invention relates to determining an estimated transfer function of an acoustic feedback path during fitting of a hearing device, such as e.g. a hearing aid or a listening device, which receives acoustic signals from an individual's surroundings, modifies the acoustic signals electronically and transmits the modified acoustic signals into the individual's ear or ear canal.
The invention may e.g. be useful in applications such as compensating for a hearing-impaired individual's loss of hearing capability, augmenting a normal-hearing individual's hearing capability or protecting an individual's hearing capability.
Many known hearing devices must be adapted or fitted to the particular individual who is to be using the hearing device, i.e. the user. Such fitting may be necessary in order to account for e.g. differing hearing capabilities and/or differing anatomic features of the ear, and typically comprises setting a maximum gain for the hearing device in order to prevent feedback-generated oscillations during use of the hearing device. Fitting is typically performed by a hearing-care professional (HCP or “dispenser”) by means of a fitting apparatus connected to the hearing device.
Patent application EP 1 708 544 discloses a system and a method for measuring vent effects in a hearing aid. During a self-test performed at the beginning of a fitting session, the hearing aid generates an electric tone signal in an electric signal path between the hearing-aid microphone and the hearing-aid loudspeaker, picks up the acoustic feedback from the loudspeaker to the microphone, and generates a correlation signal based on a comparison between the electric tone signal and the acoustic feedback. The hearing aid then calculates acoustic properties of the vent based on the correlation signal. If the calculated acoustic properties deviate from previously stored properties, the HCP is informed and may then e.g. modify the length or the diameter of the vent or lower the gain of the hearing aid.
Patent EP 1 310 138 B1 discloses a hearing aid in which the signal path between the microphone and the loudspeaker is blocked during a comfort delay period after start-up of the hearing aid in order to avoid feedback-generated oscillations during insertion of the hearing aid into the ear. During the comfort delay period, the hearing aid generates an acoustic signal in order to notify the user that the hearing aid is switched on and is operative.
It is an object of the present invention to provide improvements of the above mentioned methods, apparatus and systems.
These and other objects of the invention are achieved by the invention defined in the accompanying independent claims and as explained in the following description. Further objects of the invention are achieved by the embodiments defined in the dependent claims and in the detailed description of the invention.
In the present context, a “hearing device” refers to a device, such as e.g. a hearing aid or an active ear-protection device, which is adapted to improve, augment and/or protect the hearing capability of an individual by receiving acoustic signals from the individual's surroundings, generating corresponding audio signals, modifying the audio signals and providing the modified audio signals as audible signals to at least one of the individual's ears. Such audible signals may e.g. be provided in the form of acoustic signals radiated into the individual's outer ears, acoustic signals transferred as mechanical vibrations to the individual's inner ears through the bone structure of the individual's head and/or electric signals transferred directly or indirectly to the cochlear nerve of the individual. The hearing device may be configured to be worn in any known way, e.g. as a unit arranged behind the ear with a tube leading radiated acoustic signals into the ear canal or with a loudspeaker arranged close to or in the ear canal, as a unit entirely or partly arranged in the pinna and/or in the ear canal, as a unit attached to a fixture implanted into the skull bone, etc. More generally, a hearing device comprises an input transducer for receiving an acoustic signal from an individual's surroundings and providing a corresponding input audio signal, a signal processing circuit for processing the input audio signal and an output transducer for providing an audible signal to the individual in dependence on the processed audio signal.
A “hearing system” refers to a system comprising one or two hearing devices, and a “binaural hearing system” refers to a system comprising one or two hearing devices and being adapted to provide audible signals to both of the individual's ears with some degree of correlation. Hearing systems or binaural hearing systems may further comprise “auxiliary devices”, which communicate with the hearing devices and affect and/or benefit from the function of the hearing devices. Auxiliary devices may be e.g. remote controls, audio gateway devices, mobile phones, public-address systems, car audio systems or music players. Hearing devices, hearing systems or binaural hearing systems may e.g. be used for compensating for a hearing-impaired individual's loss of hearing capability, augmenting a normal-hearing individual's hearing capability and/or protecting an individual's hearing capability.
As used herein, the singular forms “a”, “an”, and “the” are intended to include the plural forms as well (i.e. to have the meaning “at least one”), unless expressly stated otherwise. It will be further understood that the terms “has”, “includes”, “comprises”, “having”, “including” and/or “comprising”, when used in this specification, specify the presence of stated features, integers, steps, operations, elements and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components and/or groups thereof. It will be understood that when an element is referred to as being “connected” or “coupled” to another element, it can be directly connected or coupled to the other element, or intervening elements may be present, unless expressly stated otherwise. As used herein, the term “and/or” includes any and all combinations of one or more of the associated listed items. The steps of any method disclosed herein do not have to be performed in the exact order disclosed, unless expressly stated otherwise.
The invention will be explained in more detail below in connection with preferred embodiments and with reference to the drawings in which:
The figures are schematic and simplified for clarity, and they just show details, which are essential to the understanding of the invention, while other details are left out. Throughout, like reference numerals and/or names are used for identical or corresponding parts.
Further scope of applicability of the present invention will become apparent from the detailed description given hereinafter. However, it should be understood that the detailed description and specific examples, while indicating preferred embodiments of the invention, are given by way of illustration only, since various changes and modifications within the scope of the invention will become apparent to those skilled in the art from this detailed description.
The electronic signal path 5 has an acoustic gain, which is typically both time- and frequency-dependent and is defined as the ratio between the acoustic output signal and the acoustic input signal. A portion of the acoustic output signal travels to the microphone 2 via an acoustic feedback path 8. The electronic signal path 5 and the acoustic feedback path 8 thus form a loop, in which oscillations may occur, depending on the loop gain. Such oscillations are typically perceived as annoying howling or whistling sounds or as a decreased sound quality. The transfer function of the acoustic feedback path 8 depends on properties of the hearing device 1 itself and on properties of the immediate environment of the hearing device 1, and the loop gain is thus difficult to control or predict. For instance, the transfer function typically changes radically when the hearing device 1 is inserted into or removed from the ear or when objects, such as a hand or a telephone, are moved close to the ear with the inserted hearing device 1.
The signal processor 3 is further connected to receive and transmit messages from/to the communication interface 6. Such messages may comprise e.g. mode commands to change the operating mode of the hearing device 1, settings to control the signal processing in the signal processor 3 and/or audio signals. The communication interface 6 may communicate with other apparatus, such as e.g. a remote control (not shown) or a fitting apparatus 20 (see
The signal processor 3 may preferably comprise a preamplifier 9, a digitiser 10, a digital signal processor (DSP) 11 and a digital-to-analog converter (DAC) 12, such as e.g. a pulse-width modulator, and may thus be able to process the microphone signal digitally. The preamplifier 9 is adapted to amplify the microphone signal and provide the amplified signal to the digitiser 10, which is adapted to digitise the amplified signal and provide the digitised signal to the DSP 11. The DSP 11 is adapted to process the digitised signal and provide the processed signal to the DAC 12, which is adapted to convert it into an analog signal, such as e.g. a pulse-width-modulated signal, in the modified microphone signal provided to the loudspeaker 4.
The signal processor 3 may further comprise an output signal storage 13 in which one or more audio signals may be stored. Audio signals may be stored as waveform signals or in compressed form, e.g. as commands for a signal generator (not shown) which may also be comprised in the signal processor 3 or the DSP 11. The signal processor 3 may further comprise an input signal storage 14 in which one or more microphone signals or digitised signals may be stored. Microphone signals or digitised signals may be stored as waveform signals or in compressed form, e.g. as an output from a signal analyser (not shown) which may also be comprised in the signal processor 3 or the DSP 11.
Various methods are known in the art for suppressing or preventing feedback-generated oscillations in hearing devices. Such methods comprise e.g. adaptive feedback cancelling, frequency shifting, notch-filtering and gain limiting, and any combination of such methods may be implemented in the signal processor 3 or the DSP 11. The performance of such methods may generally be improved by applying knowledge about the current value of the transfer function of the acoustic feedback path 8. For instance, an adaptive feedback canceller or an adaptive feedback cancelling system may require some time to estimate the current value of the transfer function of the acoustic feedback path 8, and this time may be shortened by using a value obtained by other means as a first estimate.
Furthermore, determination of feedback-related settings in the hearing device 1, such as e.g. a maximum gain limit and/or the amount of frequency shift, may be improved by applying knowledge about typical values of the transfer function of the acoustic feedback path 8. Such settings may be determined and transferred in messages from a fitting apparatus 20 to the hearing device 1 during a fitting session as shown in
The test period 35 thus interrupts the user-mode period 33, 36. The user-mode period 33, 36 continues till shut-down of the hearing device 1, possibly interrupted by further test periods 35. Any of the start-up period 32, the user period 33, 36 and/or the test period 35 may be interrupted for other purposes, and these time periods, 32, 33, 35, 36 need also not be adjacent to each other.
During the user-mode period 33, 36, the hearing device 1 operates in a user mode in which the hearing device 1 controls the acoustic gain G primarily as a function of levels and content of the received microphone signal. The curve G shows an example of how the acoustic gain G may vary over time. Typically, the acoustic gain G is increased in quiet environments and decreased in noisy or loud environments. The hearing device 1 may have a maximum gain setting Gmax, which limits the acoustic gain G in order to prevent feedback-generated oscillations during normal use of the hearing device 1.
During insertion of the hearing device 1 into the user's ear, the transfer function of feedback path 8 may obtain values that would cause feedback-generated oscillations even with an acoustic gain G not exceeding the maximum gain setting Gmax. In order to prevent such oscillations during the insertion, the hearing device 1 operates in a gain-reduced mode during the start-up period 32. In the gain-reduced mode, the acoustic gain G is lower than in the user-mode. For instance, the electronic signal path 5 may be blocked completely, or the acoustic gain G may be set to a value e.g. 6 dB, 10 dB, 20 dB or 30 dB lower than the maximum value of the acoustic gain G or than the maximum gain setting Gmax. The amount of lowering is preferably selected such that it effectively prevents feedback-generated oscillations in the hearing device 1 during the start-up period 32.
Since the acoustic gain G is reduced during the start-up period 32, the hearing device 1 does not provide the normal amplification of environment sounds, and the user might thus not be aware that the hearing device 1 is actually turned on. In order to signal the status of the hearing device 1 as early as possible, the hearing device 1 provides within the start-up period 32 a first predetermined audio signal 37, e.g. a start-up jingle, and transmits it via the loudspeaker 4. A portion of the transmitted acoustic signal 37 reaches the microphone 2 through the acoustic feedback path 8 as a first acoustic feedback signal 38. The microphone 2 may receive and convert the first acoustic feedback signal 38 into a corresponding first microphone signal, and the hearing device 1 may determine a first estimated transfer function of the acoustic feedback path 8 by comparing the first microphone signal and the first predetermined audio signal 37. The comparison may e.g. be made by determining the correlation between the signals at multiple frequencies. The hearing device 1 may further store the first microphone signal in the input signal storage 14 from which the hearing device 1 may retrieve it for subsequent use. The first predetermined audio signal 37 is preferably composed of a polyphonic sequence of tones and/or tonal sweeps with harmonic relations such that it provides a pleasant experience to the user.
The hearing device 1 may use the first estimated transfer function to determine initial settings for suppressing or preventing feedback-generated oscillations. The first estimated transfer function may e.g. be used as a first estimate in an adaptive feedback canceller (not shown) in the hearing device 1. In the user mode, the hearing device 1 may further control the acoustic gain G in dependence on the first estimated transfer function. Alternatively or additionally, the hearing device 1 may compare the first estimated transfer function to a previously saved transfer function, based on the comparison determine whether the insertion of the hearing device 1—and/or an ear-mould or earplug hereof—is completed, and optionally repeat the transmission of the first predetermined audio signal 37 and the determination of the first estimated transfer function until a comparison with the previously saved transfer function indicates that the insertion is completed. Alternatively or additionally, the hearing device 1 may compare the first estimated transfer function to a previously saved transfer function, and based on the comparison determine whether the acoustic feedback path has undergone long-term changes, e.g. due to blocking of a vent in the hearing device 1 or due to physical changes in the ear canal of the user—e.g. the growing of a child's ear. Such conditions may be signalled to the user by means of an appropriate acoustic warning signal. The first predetermined audio signal 37 as well as any warning signals may be stored in the output signal storage 13, e.g. during production of the hearing device 1 and/or during a fitting session, and the hearing device 1 may retrieve them therefrom when required. Instead of comparing estimated transfer functions, the hearing device 1 may for the same purposes and with the same benefits compare stored microphone signals.
The hearing device 1 is fitted to the user in a fitting session in which the hearing device 1 is connected to the fitting apparatus 20 as shown in
On receiving a predetermined message 34 that directly or indirectly indicates that a measurement of the acoustic feedback path 8 should be conducted, the hearing device 1 temporarily invokes the test period 35. Within the test period 35, the hearing device 1 provides a second predetermined audio signal 39, e.g. the start-up jingle, and transmits it via the loudspeaker 4. A portion of the transmitted acoustic signal 39 reaches the microphone 2 through the acoustic feedback path 8 as a second acoustic feedback signal 40. The microphone 2 receives and converts the second acoustic feedback signal 40 into a corresponding second microphone signal, and the hearing device 1 determines a second estimated transfer function of the acoustic feedback path 8 by comparing the second microphone signal and the first and/or the second predetermined audio signal 37, 39. The hearing device 1 may further store the second microphone signal in the input signal storage 14 for subsequent use, and in this case, determining the second estimated transfer function of the acoustic feedback path 8 may be performed by the fitting apparatus 20 instead of the hearing device 1. The hearing device 1 communicates the second estimated transfer function and/or the second microphone signal to the fitting apparatus 20, which may compute the second estimated transfer function and/or display it to the HCP.
The hearing device 1 and/or the fitting apparatus 20 may perform one or more of the comparisons performed by the hearing device 1 upon start-up as described above, this time based on the second estimated transfer function and/or the second microphone signal. Instead of comparing estimated transfer functions, the hearing device 1 and/or the fitting apparatus 20 may compare stored microphone signals in order to arrive at the same conclusions.
Additionally or alternatively, the hearing device 1 may determine the first and/or the second estimated transfer function of the acoustic feedback path 8 by means of an adaptive feedback canceller (not shown) comprised in the hearing device 1. The adaptive feedback canceller may determine the estimate(s) by comparing the first and/or second microphone signal with the first and/or second predetermined audio signal 37, 39.
The HCP and/or the fitting apparatus 20 may use the second estimated transfer function and/or the results of comparison with previously stored transfer functions or microphone signals to determine settings for the hearing device 1. Such settings may comprise settings related to feedback suppression, such as e.g. a maximum gain limit and/or the amount of frequency shift. Thus, in the user mode, the hearing device 1 may eventually control the acoustic gain G in dependence on the second estimated transfer function.
The fitting apparatus 20 preferably transmits the predetermined message 34 automatically, i.e. without intervention of the HCP, in reaction to one or more predefined events during the fitting session. Such events may e.g. be detection of a connection between the fitting apparatus 20 and the hearing device 1, start-up of a predefined program in the fitting apparatus 20 and/or initiation of a predefined part of the fitting procedure in the fitting apparatus 20.
The hearing device 1 may operate in the noise-reduced mode during the test period 35 in order to allow for a more precise determination of the second estimated transfer function. The gain reduction in the test period 35 may be less than in the start-up period 32, since at this time, the hearing device 1 should already be properly inserted into the user's ear, and thus, large variations of the acoustic feedback path 8 are unlikely to occur.
The hearing device 1 may invoke the test period 35 by restarting itself, such that a second start-up period 32 forms the test period 35, or it may invoke the test period 35 as a period independent from the start-up period 32.
The second predetermined audio signal 39 is substantially identical to the first predetermined audio signal 37. In the present context, substantial identity implies that the signals 37, 39 are derived from the same stored audio signal. This allows saving resources in the hearing device 1. Preferably, the signals 37, 39 are so identical that the user will perceive them as identical. This aids in giving the user the impression that the hearing device 1 functions in a known way in the fitting session.
The first and second predetermined audio signals 37, 39 preferably comprise a sequence of varying tones, and the hearing device 1 and/or the fitting apparatus 20 may determine the first and/or the second estimated transfer function at multiple frequencies corresponding to the tones. This further allows for providing a pleasant signal to the user.
The first and second predetermined audio signals 37, 39 preferably, additionally or alternatively, comprise one or more frequency sweeps, and the hearing device 1 and/or the fitting apparatus 20 may determine the first and/or the second estimated transfer function across one or more continuous frequency ranges.
The first and second predetermined audio signals 37, 39 are preferably polyphonic in order to allow a relatively short duration of the start-up period 32 and/or the test period 35.
Composing the first and second predetermined audio signals 37, 39 of a polyphonic sequence of tones and/or tonal sweeps, preferably with harmonic relations, increases the probability of providing a pleasant experience to the user and thus increases the probability of achieving a good fitting result.
The method may be implemented in the hearing device 1 and/or in a system comprising a fitting apparatus 20 and a hearing device 1.
The signal processor 3 is preferably implemented mainly as digital circuits operating in the discrete time domain, but any or all parts hereof may alternatively be implemented as analog circuits operating in the continuous time domain. Digital functional blocks of the signal processor 3 and/or of the communication interface 6 may be implemented in any suitable combination of hardware, firmware and software and/or in any suitable combination of hardware units. Furthermore, any single hardware unit may execute the operations of several functional blocks sequentially, in parallel or in interleaved sequence and/or in any suitable combination thereof.
Further modifications obvious to the skilled person may be made to the disclosed method, system, apparatus and/or device without deviating from the scope of the invention. Within this description, any such modifications are mentioned in a non-limiting way. The possible modifications below are mentioned as examples hereof.
Some preferred embodiments have been described in the foregoing, but it should be stressed that the invention is not limited to these, but may be embodied in other ways within the subject-matter defined in the following claims. For example, the features of the described embodiments may be combined arbitrarily, e.g. in order to adapt the system, the apparatus, the devices and/or the method according to the invention to specific requirements.
It is further intended that the structural features of the system, apparatus and/or devices described above, in the detailed description of ‘mode(s) for carrying out the invention’ and in the claims can be combined with the methods, when appropriately substituted by a corresponding process. Embodiments of the methods have the same advantages as the corresponding systems and/or devices.
Any reference numerals and names in the claims are intended to be non-limiting for their scope.
| Number | Date | Country | Kind |
|---|---|---|---|
| 12166326 | May 2012 | EP | regional |
| Number | Name | Date | Kind |
|---|---|---|---|
| 20030161492 | Miller | Aug 2003 | A1 |
| 20050226447 | Miller, III | Oct 2005 | A1 |
| 20060285709 | Barthel | Dec 2006 | A1 |
| 20080031479 | Sorgel | Feb 2008 | A1 |
| 20100166198 | Perman | Jul 2010 | A1 |
| Number | Date | Country |
|---|---|---|
| 1 310 138 | Sep 2006 | EP |
| 1 708 544 | Oct 2006 | EP |
| 1 737 270 | Dec 2006 | EP |
| 1 885 158 | Feb 2008 | EP |
| Number | Date | Country | |
|---|---|---|---|
| 20130294610 A1 | Nov 2013 | US |
| Number | Date | Country | |
|---|---|---|---|
| 61641312 | May 2012 | US |
