WO2010021125A1 - 補聴器および補聴器システム - Google Patents
補聴器および補聴器システム Download PDFInfo
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- WO2010021125A1 WO2010021125A1 PCT/JP2009/003931 JP2009003931W WO2010021125A1 WO 2010021125 A1 WO2010021125 A1 WO 2010021125A1 JP 2009003931 W JP2009003931 W JP 2009003931W WO 2010021125 A1 WO2010021125 A1 WO 2010021125A1
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- hearing aid
- sound
- signal
- setting
- input signal
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- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
- H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
Definitions
- the present invention relates to a hearing aid and a hearing aid system, and more particularly, to a hearing aid and a hearing aid system that can simplify setting (volume / operation mode) of the hearing aid.
- Hearing aids are required to improve the audibility of speech and the like according to the distinction between speech and non-speech, ambient noise, noise or reverberation, and to reproduce highly clear speech regardless of the sound environment.
- hearing aids in which a volume change button and an operation mode change button are added to the hearing aid body, and the hearing aid wearer can consciously change settings according to the usage scene and sound environment (for example, Patent Document 1).
- FIG. 12 is a block diagram showing a configuration example of such a remote control hearing aid system.
- This remote control hearing aid system has a telephone 10 and a hearing aid 40.
- the call detection unit 6 of the telephone 10 detects that the call is in progress.
- the control signal generating unit 5 generates a control signal.
- the control signal and the reception signal are converted into an acoustic signal by the electroacoustic conversion unit 4 and transmitted to the hearing aid 40.
- the transmitted acoustic signal is received by the sound wave receiving unit 41 on the hearing aid 40 side and converted into a received signal which is an electrical signal.
- the reception signal converted by the sound wave reception unit 41 is sent to the power amplification unit 44 and the analysis control unit 46 through the reception switching unit 43.
- the received received signal is frequency-analyzed and compared with the stored signal in the analysis control unit 46 to generate a control signal.
- the control signal is sent to the power amplifier 44 and used to change the amplification factor of the received signal (see, for example, Patent Document 4).
- the volume change button and the operation mode change button are small, and when the hearing aid is worn, the buttons are not directly visible, and it is difficult to change the setting. There is a problem of being.
- there is a technique for automatically changing the setting of the hearing aid according to the sound environment but there is an advantage that the operation is unnecessary, but there is also a problem that the setting does not necessarily match the user's intention.
- there is a technique for changing the setting by a device other than the hearing aid main body but there is a restriction that the setting change cannot be performed when the user intends unless the other device is always carried. It also adjusts acoustic parameters using an external device such as a server, database, or telephone for adjusting the hearing aid. When adjusting acoustic parameters using an external device, the adjustment sound is harsh when setting with a mobile phone. I sometimes felt uncomfortable.
- the present invention has been made in view of the above-described conventional circumstances, and the user can reflect the change in the setting of the hearing aid according to the sound environment as intended, and the user can feel inconvenience and discomfort due to the change in the setting of the hearing aid. It is another object of the present invention to provide a hearing aid and a hearing aid system that can further simplify setting changes.
- the hearing aid of the present invention includes a microphone that generates an input signal from an input sound, a signal processing unit that generates an output signal from the input signal, and a receiver that reproduces the output sound from the output signal, and the signal processing unit includes: In a predetermined time interval, the time response of the input signal based on the contact sound generated when the hearing aid is touched is determined, and the setting of the hearing aid is changed based on the time response.
- the hearing aid since the time response of the input signal is determined and the setting of the hearing aid is changed based on the time response, the hearing aid can be operated without operating the buttons of the downsized hearing aid and without using another device. It is possible to easily change the hearing aid settings (sound parameters such as volume and operation mode).
- the signal processing unit calculates the intensity of the input signal, an average value of the input signal in a predetermined time interval is equal to or less than a first predetermined threshold, and the predetermined time
- the setting of the hearing aid is changed by detecting at least twice when the intensity of the input signal in the section becomes equal to or higher than a second predetermined threshold.
- the setting is changed by detecting at least twice when the intensity of the input signal is equal to or higher than the second predetermined threshold. Therefore, the setting of the hearing aid is reliably changed even in a noisy normal environment. be able to.
- the signal processing unit sets a time width for detecting when the intensity of the input signal becomes equal to or higher than the second predetermined threshold.
- the contact sound is a sound played by a toe or a toe tap sound
- the signal processing unit sets the time width to 20 msec or less.
- the signal processing unit reduces the signal intensity with respect to a time width in which the signal processing unit detects a time point when the intensity of the input signal becomes equal to or higher than the second predetermined threshold.
- the intensity of the input signal is reduced with respect to the time width in which the case where the intensity of the input signal is equal to or greater than the second predetermined threshold is detected. Therefore, when changing the setting of the hearing aid, No discomfort to the person.
- the signal processing unit calculates the intensity of the input signal, an average value of the input signal in a predetermined time interval is equal to or less than a first predetermined threshold, and the input signal Is changed into a frequency domain signal, and the setting of the hearing aid is changed by detecting at least twice when the difference between the waveform of the frequency domain signal and the waveform of the predetermined signal falls below a third predetermined threshold value.
- the setting is changed by detecting at least twice when the difference between the waveform of the frequency signal and the waveform of the predetermined signal is equal to or smaller than the third predetermined threshold, it is ensured even in a normal environment with noise. Hearing aid settings can be changed.
- the signal processing unit sets a time width for detecting a time point when a difference between the waveform of the signal in the frequency domain and the waveform of the predetermined signal is equal to or less than the third predetermined threshold.
- the contact sound is a sound played by a toe or a toe tap sound
- the signal processing unit sets the time width to 20 msec or less.
- the signal processing unit outputs a signal with respect to a time width in which the difference between the waveform of the signal in the frequency domain and the waveform of the predetermined signal is less than or equal to the third predetermined threshold. Reduce strength.
- the intensity of the input signal is reduced with respect to the detected time width when the difference between the waveform of the frequency signal and the waveform of the predetermined signal is equal to or smaller than the third predetermined threshold. There is no discomfort to the hearing aid wearer when making changes.
- the signal processing unit notifies that the setting of the hearing aid has been changed.
- the anxiety of the hearing aid wearer regarding whether or not the setting change has been made can be eliminated.
- the hearing aid system of the present invention is a hearing aid system having a hearing aid and a hearing aid setting device for changing the setting of the hearing aid
- the hearing aid setting device includes an input unit for inputting the setting of the hearing aid, A storage unit that stores a mask sound indicating an adjustment sound to be output when changing the setting, and masker sound information for masking the maski sound, the masker sound and maski sound stored in the storage unit, and the The hearing aid is reproduced by the hearing aid setting device, comprising: a signal synthesis unit that generates an output signal based on the setting of the hearing aid input by the input unit; and a speaker that reproduces a set sound from the output signal.
- a microphone that generates a setting signal from the set sound, and the masking sound is extracted from the setting signal, and the setting of the hearing aid is extracted from the extracted masking sound.
- a signal processing unit for changing the setting of the hearing aid on the basis of the hearing aid settings.
- the signal intensity of the signal indicating the mask sound is equal to or lower than the signal intensity of the signal indicating the masker sound.
- the masking sound is set to be equal to or lower than the masking level of the masking sound, so that an harsh adjustment sound is not heard at the time of setting, and the hearing aid wearer is not uncomfortable.
- the mask sound is a pure tone.
- the masking circuit configuration can be simplified by making the mask sound a pure tone.
- the signal processing unit of the hearing aid notifies that the setting of the hearing aid has been changed.
- the anxiety of the hearing aid wearer regarding whether or not the setting change has been made can be eliminated.
- the masker sound includes frequency components other than the frequency components included in the mask sound.
- the signal processing unit calculates the intensity of the input signal, an average value of the input signal in a predetermined time interval is equal to or less than a first predetermined threshold, and the predetermined time The number of times that the intensity of the input signal in the section becomes equal to or greater than a second predetermined threshold is detected, and a plurality of settings of the hearing aid are identified and changed based on the number of times.
- a plurality of settings can be easily identified and changed according to the number of times without performing a button operation.
- the hearing aid of the present invention includes a first microphone that generates a first input signal from an input sound, a second microphone that generates a second input signal from the input sound, an output from the first input signal and the second input signal.
- a signal processing unit that generates a signal; and a receiver that reproduces output sound from the output signal, wherein the signal processing unit is configured to perform the first input based on contact sound generated when the hearing aid is touched in a predetermined time interval. Determining a time response of the signal and the second input signal and identifying and changing a plurality of settings of the hearing aid based on the time response.
- the time response of the two input signals is determined and the setting of the hearing aid is changed based on the time response, another device is used without operating the downsized hearing aid button. It is possible to easily change the settings (acoustic parameters such as volume and operation mode) of the hearing aid with just the hearing aid. Furthermore, it is possible to easily identify and change a plurality of settings based on the time responses of the two input signals without performing a button operation.
- the signal processing unit compares the amplitude values of the first input signal and the second input signal, and identifies and changes a plurality of settings of the hearing aid based on the amplitude value. To do.
- a plurality of different settings (for example, a setting for increasing the volume and a setting for decreasing the volume) can be performed when the contact sound is input only to the first microphone and when the contact sound is input only to the second microphone. it can.
- the signal processing unit determines a time difference between amplitude peak times of the first input signal and the second input signal, and based on the time difference of the amplitude peak time, a plurality of the hearing aids Identify and change settings.
- the present invention makes it possible to easily change the settings (acoustic parameters such as volume and operation mode) of the hearing aid with only the hearing aid without operating the buttons of the miniaturized hearing aid and without using another device. Can do.
- the hearing aid setting is extracted from the extracted mask sound and the setting is changed based on the extracted hearing aid setting, an harsh adjustment sound is not heard at the time of setting, and the hearing aid wearer is not uncomfortable.
- the block diagram which shows an example of schematic structure of the hearing aid concerning the 1st Embodiment of this invention The block diagram which shows an example of the internal structure of the signal processing part in the hearing aid of the 1st Embodiment of this invention.
- the figure which shows an example of the time response at the time of applying a masticatory sound to an ear hook type hearing aid as operation of a hearing aid wearer in the 1st Embodiment of this invention (a measurement place is an auricle upper part).
- the figure which shows an example of a time response at the time of applying a masticatory sound to an ear hole type hearing aid as operation of a hearing aid wearer in the 1st Embodiment of this invention (a measurement place is in an ear canal).
- the block diagram which shows the structural example of the conventional remote control hearing aid system
- the block diagram which shows an example of schematic structure of the hearing aid concerning the 3rd Embodiment of this invention.
- the hearing aid wearer detects the sound (contact sound) that the hearing aid wearer touches the hearing aid body, and the setting is changed (acoustic parameter is changed).
- the setting of the hearing aid is changed when the amplitude fluctuation of the input signal exceeds a signal equal to or greater than the second threshold value at least twice in a section (for example, no noise) equal to or less than the first threshold value. That is, in a predetermined time interval, the time response of the input signal based on the contact sound generated when touching the hearing aid is determined, and the setting of the hearing aid is changed based on this time response.
- the frequency characteristics of the input signal may be limited.
- the acoustic parameters include an environmental parameter indicating the environment around the hearing aid, an output parameter indicating the output level of the hearing aid, a noise suppression parameter indicating a suppression level for suppressing noise around the hearing aid, and the like.
- setting and changing acoustic parameters may be simply referred to as setting and changing.
- the contact sound includes a sound that a hearing aid wearer has played the hearing aid body with a toe, a toe tap sound, a buzzing microphone, and the like.
- sounds generated in the body of a hearing aid wearer may be used.
- the reproduced sound from the adjusting device is a masker sound (masked sound)
- the hearing aid adjusted sound is a mask sound (masked sound)
- the hearing aid adjusted sound is Make it inconspicuous.
- the hearing aid adjustment sound is set to be equal to or lower than the masking level of the masker sound (reproduced sound).
- FIG. 1 is a block diagram showing an example of a schematic configuration of a hearing aid according to the first embodiment of the present invention.
- a hearing aid 100 shown in FIG. 1 includes a microphone 101 that generates an input signal from an input sound, an A / D conversion unit 111 that converts the input signal into a digital signal, and a signal processing unit that processes the input signal to generate an output signal. 120, a hearing aid signal processing unit 118 that adjusts the frequency characteristics or the like of an audio signal as an input signal, that is, controls the frequency characteristics, a D / A conversion unit 119 that converts a digital signal into an analog signal, And a receiver 103 that reproduces output sound from an output signal that is an A-converted analog signal.
- the signal processing for the hearing aid includes, for example, nonlinear compression processing that amplifies an audio signal input at a different amplification factor for each frequency, noise suppression processing that suppresses a noise component input from the microphone 101, and the like. .
- This signal processing for the hearing aid can be performed based on acoustic parameters as hearing aid settings.
- the signal processing unit 120 includes a signal strength calculation unit 121 that calculates the strength of the input signal, a threshold storage unit 123 that stores a predetermined threshold for comparison with the signal strength of the input signal, and the signal strength of the input signal and the predetermined level.
- a signal strength comparison unit 124 that compares threshold values, a signal determination unit 125 that determines a time response of an input signal based on a predetermined threshold value and a comparison result, and a setting control unit 126 that changes the setting of the hearing aid based on the determination of the time response And have.
- the signal determination unit 125 determines at least two points when the average value of the input signal strength within the predetermined time interval is equal to or lower than the first predetermined threshold value and the input signal strength within the predetermined time interval is equal to or higher than the second predetermined threshold value. When detected once, a signal for changing the setting of the hearing aid is output to the setting control unit 126.
- the signal determination unit 125 can set a time width for detecting a point in time when the input signal intensity in the predetermined time interval becomes equal to or higher than the second predetermined threshold.
- a contact sound to the hearing aid body by a hearing aid wearer a sound generated when the hearing aid body is played with the tip of the toe (this is expressed as ⁇ sound played with the tip of the toe '') or a sound generated when the hearing aid body is hit with the toe (This is expressed as “toe tap sound”).
- the time width from the start to the end of the sound played by the toe or the toe tap sound as one contact sound can be set to, for example, 5 msec or more and 20 msec or less.
- the frequency analysis processing function of the signal processing unit 120 can be developed to be less than 5 msec.
- the time width of the sound of stroking the microphone and the sound generated in the body becomes longer.
- the time width for detecting the sound played by the toe or the toe tap sound may be as short as possible, for example, 1 msec. By shortening the time width in order to detect the contact sound, it is possible to accurately detect the temporal rise in amplitude due to the contact sound.
- the signal determination unit 125 determines that the signal is for setting a hearing aid, the signal is input to the setting control unit 126 as a setting signal, and the setting control unit 126 changes the setting of the hearing aid.
- the signal processing unit 120 detects the time when the input signal intensity is equal to or higher than the second predetermined threshold within the predetermined time interval.
- the signal strength can be reduced with respect to the width.
- a method for reducing the signal strength a method of converting the input signal strength below the first predetermined threshold, a method of converting the input signal strength below the second predetermined threshold, or within a predetermined time interval, A method of converting to a sound pressure level equivalent to a time interval in which no contact sound is generated can be considered.
- the method for suppressing the signal intensity for example, a method described in Japanese Patent Laid-Open No. 1-149508 is applied, or a shock sound suppressing method described in Japanese Patent Laid-Open No. 6-276599 is applied. You can do it.
- the output from the signal processing unit 120 is a signal obtained by reducing the signal intensity of the contact sound generated in order to change the setting of the hearing aid for the output signal of the A / D conversion unit 111, and the signal processing unit for the hearing aid It is assumed that 118 is input.
- the hearing aid signal processing unit 118 performs signal processing necessary as a hearing aid, such as directivity synthesis processing, noise suppression processing, howling suppression processing, and nonlinear compression processing.
- the hearing aid signal processing unit 118 when the signal processing determination unit 125 determines that the signal is for setting a hearing aid, and the setting control unit 126 changes the setting, the hearing aid user is notified that the setting change has been completed.
- Add a signal for As an example of the notification method for example, it is conceivable to generate a notification sound or notify by voice.
- the signal processing unit 120 can be configured as shown in FIG. 2 instead of FIG.
- the signal processing unit 120 shown in FIG. 2 converts an input signal into data in the frequency domain by performing a fast Fourier transform (Fast Fourier Transform), A spectrum comparison unit 202 that compares spectra of data in the frequency domain is added. That is, the signal processing unit 120 in FIG. 1 determines the time response, but the signal processing unit 120 in FIG. 2 determines the frequency component of the input signal.
- Fast Fourier Transform Fast Fourier transform
- the signal determination unit 125 converts the input signal into a frequency domain signal whose average value of the input signal strength within the predetermined time interval is equal to or less than the first predetermined threshold, and the frequency domain signal waveform and the predetermined signal
- the time point at which the difference from the waveform is equal to or less than the third predetermined threshold is detected at least twice, the setting of the hearing aid is changed. That is, the setting of the hearing aid is changed according to the analysis result of the frequency domain signal.
- the waveform of the predetermined signal is stored in the threshold storage unit 123.
- the signal determination unit 125 sets a time width for detecting a time point when the difference between the waveform of the signal in the frequency domain and the waveform of the predetermined signal is equal to or less than a third predetermined threshold. can do.
- a sound played by a toe or a toe tap sound is used as a contact sound to a hearing aid body by a hearing aid wearer.
- the time width from the start to the end of the sound played by the toe or the toe tap sound as one contact sound can be set to 20 msec or less, for example. Note that the time width of the sound of stroking the microphone and the sound generated in the body becomes longer.
- the signal determination unit 125 determines that the signal is for setting a hearing aid, the signal is input to the setting control unit 126 as a setting signal, and the setting control unit 126 changes the setting of the hearing aid.
- the signal processing unit 120 determines that the difference between the waveform of the frequency signal and the waveform of the predetermined signal is a third predetermined value within a predetermined time interval.
- the signal intensity can be reduced with respect to the time width in which the time point when the threshold value is not reached is detected.
- a method for reducing the signal strength a method for converting the input signal strength to less than a first predetermined threshold, or a sound pressure level equivalent to a time interval in which no contact sound is generated within a predetermined time interval. A method of conversion can be considered.
- the output from the signal processing unit 120 is a signal obtained by reducing the signal intensity of the contact sound generated in order to change the setting of the hearing aid for the output signal of the A / D conversion unit 111, and the signal processing unit for the hearing aid It is assumed that 118 is input.
- the hearing aid signal processing unit 118 performs signal processing necessary as a hearing aid, such as directivity synthesis processing, noise suppression processing, howling suppression processing, and nonlinear compression processing.
- the hearing aid signal processing unit 118 when the signal determination unit 125 determines that the signal is for setting a hearing aid, and the setting control unit 126 changes the setting, to notify the hearing aid wearer that the setting change has been completed. Is added.
- the notification method for example, it is conceivable to generate a notification sound or notify by voice.
- the signal determination unit 125 may have a plurality of determination criteria. . For example, when discriminating the setting for increasing the volume and the setting for decreasing the volume, the signal determination unit 125 determines that the average value of the input signal intensity within the predetermined time interval is equal to or less than the first predetermined threshold and the predetermined time interval. When the input signal intensity in the signal becomes greater than or equal to the second predetermined threshold, it can be determined that the volume is increased if it is detected twice, and it can be determined that the volume is decreased if it is detected three times or more. That is, a plurality of settings of the hearing aid 100 can be identified and changed based on the detected number of times. By doing so, the intention of the hearing aid wearer to change the setting can be identified by the signal determination unit 125 of the hearing aid.
- the type of contact sound generated by different operations on the hearing aid 100 by the hearing aid wearer for example, the sound played by the toe, the toe tap sound, the buzzing sound with the finger pad, the sound generated in the body, the amplitude of the signal and the time It can be considered that it is used as another control signal by discriminating it from fluctuations, frequency characteristics and the like. Accordingly, the signal determination unit 125 of the hearing aid 100 can identify the intention of the hearing aid wearer to change the setting. Accordingly, it is possible to identify and change a plurality of settings, and it is possible to reduce the number of setting change operations of the hearing aid wearer and to avoid an unintended setting change.
- the time response of the input signal is determined, and the setting of the hearing aid is changed based on the time response. It is possible to easily change the settings (acoustic parameters such as volume and operation mode) of the hearing aid by using only the hearing aid without using the above device. In particular, when an elderly person is a hearing aid wearer, it is very useful because it is difficult to operate a miniaturized hearing aid.
- the time response when various contact sounds are input to the hearing aid of the present embodiment will be described.
- a hearing aid an ear hook type hearing aid or a small ear hook type hearing aid is used.
- the ear-hook type hearing aid refers to one whose overall length of the hearing aid main body (the main body refers to the main body portion excluding the hanger part and the tube part) is approximately 3 cm or more, and the small ear-type hearing aid is a hearing aid.
- the total length of the main body is less than about 3 cm.
- FIG. 5 shows a graph when a sound played by a toe (an example of a contact sound) is applied to an ear-hook type (experimental model A) as a hearing aid wearer's operation.
- 5A shows the time response of the input signal amplitude.
- the horizontal axis indicates time (unit: seconds), and the vertical axis indicates the sound pressure level (here, the maximum input sound pressure level is expressed as 0 dB).
- b) is an enlarged view in the time direction of an impulse waveform as a time response, where the horizontal axis represents time (unit: millisecond), and the vertical axis represents sound pressure level.
- FIG. 5C shows frequency characteristics of time response, where the horizontal axis represents frequency (unit: Hz) and the vertical axis represents sound pressure level.
- th1 (-15 dB line) represents an example of a first predetermined threshold
- th2 (-9 dB line) represents an example of a second predetermined threshold
- ti indicates an example of a predetermined time interval
- d indicates an example of a time width.
- FIG. 6 shows a graph when a sound played by a toe (an example of a contact sound) as an operation of a hearing aid wearer is applied to a small ear hook type (experimental model B) hearing aid.
- 6A shows the time response of the input signal amplitude
- the horizontal axis shows time (unit: second)
- the vertical axis shows the sound pressure level
- FIG. 6B shows the time response of the impulse waveform in the time direction. It is an enlarged view, the horizontal axis is time (unit is millisecond), and the vertical axis is sound pressure level.
- FIG. 6C shows frequency characteristics of time response, where the horizontal axis represents frequency (unit: Hz) and the vertical axis represents sound pressure level.
- the sound played by the toe has a high sound pressure level. Understandable. Therefore, when these hearing aids are played with the toes, the sound pressure level surely exceeds the second predetermined threshold value, and the settings of the hearing aids can be reliably changed.
- FIG. 7 shows a graph in the case where a tap sound (an example of a contact sound) that is a sound of hitting with a toe is applied to a hearing aid type (experimental model A) as an operation of a hearing aid wearer.
- 7A shows the time response of the input signal amplitude
- the horizontal axis indicates time (unit: seconds)
- the vertical axis indicates the sound pressure level
- FIG. 7B shows the time response of the impulse waveform in the time direction. It is an enlarged view, the horizontal axis is time (unit is millisecond), and the vertical axis is sound pressure level.
- FIG. 7C shows frequency characteristics of time response, where the horizontal axis represents frequency (unit: Hz) and the vertical axis represents sound pressure level.
- FIG. 8 shows a graph in the case of applying a tap sound (an example of a contact sound) that is a sound of tapping with a toe as an operation of a hearing aid wearer to a hearing aid of a small ear hook type (experimental model B).
- 8A shows the time response of the input signal amplitude
- the horizontal axis shows time (unit: second)
- the vertical axis shows the sound pressure level
- FIG. 8B shows the time response of the impulse waveform in the time direction. It is an enlarged view, the horizontal axis is time (unit is millisecond), and the vertical axis is sound pressure level.
- FIG. 8C shows frequency characteristics of time response, where the horizontal axis represents frequency (unit: Hz) and the vertical axis represents sound pressure level.
- FIG. 9 shows a graph in the case of applying a buzzing sound with a finger pad (an example of a contact sound) to the hearing aid as an operation of the hearing aid wearer.
- 9A shows the time response of the input signal amplitude
- the horizontal axis shows time (unit: seconds)
- the vertical axis shows the sound pressure level
- FIG. 9B shows the time response of the impulse waveform expanded in the time direction.
- the horizontal axis represents time (unit: milliseconds)
- the vertical axis represents sound pressure level.
- FIG. 9C shows frequency characteristics of time response, where the horizontal axis represents frequency (unit: Hz) and the vertical axis represents sound pressure level.
- FIG. 10 shows a graph when a masticatory sound (an example of contact sound) is applied to an ear-mounted hearing aid as an operation of a hearing aid wearer (measurement location is at the upper part of the auricle).
- 10A shows the time response of the input signal amplitude
- the horizontal axis shows time (unit: seconds)
- the vertical axis shows sound pressure level
- FIG. 10B shows the time response of the impulse waveform in the time direction.
- the horizontal axis represents time (unit: milliseconds)
- the vertical axis represents sound pressure level.
- FIG. 10C shows frequency characteristics of time response, where the horizontal axis represents frequency (unit: Hz) and the vertical axis represents sound pressure level.
- FIG. 11 shows a graph when a masticatory sound (an example of contact sound) is applied to an ear hole type hearing aid as an operation of a hearing aid wearer (measurement location is in the ear canal).
- 11A shows the time response of the input signal amplitude
- the horizontal axis shows time (unit: second)
- the vertical axis shows the sound pressure level
- FIG. 11B shows the time response of the impulse waveform in the time direction.
- the horizontal axis represents time (unit: milliseconds)
- the vertical axis represents sound pressure level.
- FIG. 11C shows frequency characteristics of time response, where the horizontal axis represents frequency (unit: Hz) and the vertical axis represents sound pressure level.
- the hearing aid for example, if a hearing aid wearer plays the hearing aid with a toe or a tap sound as an input signal, the case where the intensity of the input signal exceeds a predetermined threshold is reliably detected. It is possible to change the settings (acoustic parameters such as volume and operation mode) of the hearing aid reliably even in a normal environment with noise. It is easiest to detect the sound played with the toe, and then the tap sound. Therefore, it is most preferable that the sound played with the toe is a contact sound, and then a tap sound is preferable.
- FIG. 3 is a block diagram showing an example of a schematic configuration of a hearing aid system according to the second embodiment of the present invention.
- the hearing aid system of this embodiment includes a hearing aid setting device 400 and a hearing aid 100.
- the hearing aid setting device 400 includes a setting selection unit 401 to which a predetermined setting of the hearing aid is input, a masker sound storage unit 403 that stores a masker sound (sound to be masked), and a maske sound that stores a maski sound (sound to be masked).
- a sound storage unit 404 a set sound synthesizer 405 that synthesizes a set sound from a masker sound and a maski sound based on the hearing aid settings, a D / A converter 407 that converts the set sound into an analog signal, and outputs the set sound And a speaker 408.
- a set sound synthesizer 405 that synthesizes a set sound from a masker sound and a maski sound based on the hearing aid settings
- a D / A converter 407 that converts the set sound into an analog signal, and outputs the set sound And a speaker 408.
- symbol is attached
- masking refers to a phenomenon in which a certain sound becomes difficult to hear due to the presence of another sound, such as when talking in a noisy environment.
- the masker sound may be a ringtone when the setting device is a mobile phone, for example.
- the mask sound is an adjustment sound that is output when changing the setting of the hearing aid, for example, and is a conventional setting sound such as “beep”.
- the hearing aid wearer does not feel uncomfortable when setting the hearing aid.
- you may comprise so that a masker sound can be set suitably according to a hearing aid wearer's liking.
- the setting sound is a sound including a ring tone and a conventional setting sound when the setting device is a mobile phone, for example. If the setting device is a mobile phone, the setting sound obtained by synthesizing the mask sound and masker sound is downloaded in advance from the server to the mobile phone, and the setting sound is played back on the mobile phone to change the setting of the hearing aid. The form to do is also considered.
- the setting sound synthesis unit 405 adds the masking sound storage unit to the masking sound stored in the masking sound storage unit 404 in accordance with the hearing aid setting supplied from the setting selection unit 401.
- the masker sound stored in 403 is synthesized, and an output signal output from the speaker 408 as a set sound is generated.
- the masker sound and the maski sound are generated in advance by a sound source generation device that can adjust and output the frequency and sound pressure level.
- the sound generator When the sound generator generates the masker sound, the masker sound may select a sound source that does not include the frequency component included in the maski sound, that is, a sound source that includes a frequency component other than the frequency component included in the maski sound. desirable.
- the sound source generation device when the sound source generation device generates a masker sound, it is possible to reduce discomfort for the hearing aid wearer by selecting a sound that is not harsh, such as music.
- the masker sound generated in this way is stored in the masker sound storage unit 403.
- the sound source generation device when the sound source generation device generates a mask sound, there are a case where it has a single frequency component and a case where it has a plurality of frequency components.
- the sound source generation device when it has a single frequency component and a case where it has a plurality of frequency components.
- the amount of calculation of signal processing can be reduced.
- the set sound can be shortened.
- the maski sound generated in this way is stored in the maski sound storage unit 404.
- the hearing aid 100 includes a microphone 101 that picks up the setting sound 410, an A / D conversion unit 111 that converts the setting sound 410 into a digital signal, and a setting change signal processing unit 420 that extracts the hearing aid setting from the setting sound.
- a hearing aid signal processing unit 118 that adjusts frequency characteristics and the like of the audio signal
- a D / A conversion unit 119 that converts the digital signal into an analog signal
- a receiver that reproduces output sound from the output signal that is the converted analog signal 103.
- the microphone 101 detects the setting sound 410 output from the speaker 408, and the A / D conversion unit 111 converts the setting sound 410 into a digital signal (setting signal).
- the setting change signal processing unit 420 extracts a mask sound from the setting signal, and further extracts a hearing aid setting from the mask sound to change the setting of the hearing aid.
- the masking sound can be set below the masking level of the masking sound. That is, the signal intensity of the signal indicating the masker sound can be made smaller than the signal intensity of the signal indicating the masker sound.
- the mask sound can be a pure sound (single frequency sound). By making the mask sound a pure tone, the amount of signal information is reduced and the processing load is reduced.
- FIG. 4 is a schematic diagram illustrating an example of an internal configuration of the setting change signal processing unit 420.
- the setting change signal processing unit 420 stores an FFT unit 201 that converts the input signal into frequency domain data by performing fast Fourier transform (Fast Fourier Transform), and a predetermined threshold value for comparison with the signal strength of the input signal.
- FFT unit 201 that converts the input signal into frequency domain data by performing fast Fourier transform (Fast Fourier Transform), and a predetermined threshold value for comparison with the signal strength of the input signal.
- FFT unit 201 that converts the input signal into frequency domain data by performing fast Fourier transform (Fast Fourier Transform), and a predetermined threshold value for comparison with the signal strength of the input signal.
- FFT unit 201 that converts the input signal into frequency domain data by performing fast Fourier transform (Fast Fourier Transform), and a predetermined threshold value for comparison with the signal strength of the input signal.
- a maski sound extraction unit 502 that extracts
- the hearing aid 100 stores the maski sound itself or the characteristics of the maski sound (for example, the frequency component and the frequency signal level), and the maski sound extraction unit 502 sets based on the stored contents. Extract Masuki sound from the sound.
- the maski sound extraction unit 502 pays attention to the feature (for example, frequency component) of the maski sound from the signal for each frequency component that is the output of the FFT unit 201, and information about whether the maski sound is included (for example, maski sound) Extract flag).
- the masking sound can be extracted by adding a restriction not including the frequency component included in the masking sound to the masking sound.
- the signal determination unit 503 calculates the setting change content for the hearing aid based on the extracted mask sound.
- a predetermined threshold is set for the frequency band corresponding to the masking sound on the frequency axis, and the predetermined threshold is exceeded at least twice on the time axis. Then, it is determined that the hearing aid setting is changed.
- at least twice or more is set for the purpose of preventing malfunction.
- the masking sound may be a combination of a plurality of pure sounds.
- the signal determination unit 503 sets a predetermined threshold for a plurality of pure tones, and when all or one of the plurality of pure tones exceeds the predetermined threshold, the setting change of the hearing aid is performed. to decide. As described above, when a plurality of pure tones are used, it is possible to omit the process of detecting at least twice on the time axis for the purpose of preventing malfunction.
- the hearing aid setting is extracted from the extracted mask sound, and the setting is changed based on the extracted hearing aid setting. There is no discomfort to the wearer.
- the purpose of the hearing aid according to the third embodiment of the present invention is to reduce the number of setting changes for the hearing aid wearer and to prevent setting changes unintended by the hearing aid wearer.
- the volume is temporarily reduced as a patrol setting and the upper limit is reached and then the lower limit of the volume is switched even though the hearing aid wearer desires to reduce the volume.
- FIG. 13 is a block diagram showing an example of a schematic configuration of a hearing aid according to the third embodiment of the present invention.
- the difference between the third embodiment and the first embodiment of the present invention is that the hearing aid 100 shown in FIG. 1 has only one microphone 101, whereas in FIG. 13, the front microphone 101F and the rear microphone are different.
- 101R is a two-microphone configuration.
- a configuration in which two microphones are mounted on a hearing aid is generally used as a configuration for realizing a directivity synthesis function that makes it easier to hear the forward sound by suppressing the backward sound.
- the description of the same part as FIG. 1 in which one microphone is mounted will be omitted, and the signal processing unit 120 which is a part different from FIG. 1 will be described.
- the front microphone 101F is arranged on the front side in the forward direction shown in FIGS. 14 to 17 when the hearing aid 100 is attached to the ear of the hearing aid wearer, and the rear microphone 101R is connected to the hearing aid 100 by the hearing aid wearer. When placed on the ear of the user, it is arranged on the rear side in the forward direction shown in FIGS.
- the signal processing unit 120 receives input signals from the front microphone 101F and the rear microphone 101R.
- a signal strength calculation unit 121, a threshold storage unit 123, a signal strength comparison unit 124, and a signal determination unit 125 are components that perform the same processing as in FIG. 1.
- the front and rear microphone signal comparison unit 610 compares the determination result for the input signal at the front microphone 101F with the determination result for the input signal at the rear microphone 101R.
- the processing of the front / rear microphone signal comparison unit 610 will be described with reference to FIGS. 14, 15, 16, and 17.
- FIG. The settings identified by the front and rear microphone signal comparison unit 610 are reflected in the setting control unit 126.
- the signal processing unit 120 determines the time response of the input signal from the front microphone 101F and the input signal from the rear microphone 101R based on the contact sound generated when the hearing aid 100 is touched in a predetermined time interval. Then, based on the determined time response, the plurality of settings of the hearing aid 100 are identified and changed. As the plurality of settings, for example, a change setting for increasing the volume and a change setting for decreasing the volume can be considered.
- FIG. 14, FIG. 15, FIG. 16 and FIG. 17 are views showing the operation of the hearing aid wearer with two microphones on the ear-type hearing aid 100 in the hearing aid according to the third embodiment of the present invention.
- 15 (a), FIG. 16 (a), FIG. 17 (a), and FIGS. 14 (b) and 15 showing examples of time responses of input signals from the front microphone 101F and the rear microphone 101R of the hearing aid 100. It is the figure which divided and described (b), FIG.16 (b), and FIG.17 (b) for each operation.
- FIGS. 14 and 15 show a case where the hearing aid wearer strikes or plays the vicinity of the microphone 101 of the hearing aid 100 with a fingernail as an operation for changing the setting.
- FIGS. 14 and 15 show a case where the hearing aid wearer strikes or plays the vicinity of the microphone 101 of the hearing aid 100 with a fingernail as an operation for changing the setting.
- 16 and 17 show a case where the hearing aid wearer rubs or strokes the vicinity of the microphone 101 of the hearing aid with the fingernail or the belly of the finger as an operation for changing the setting. 14 to 17, description will be made with a hook-type hearing aid.
- the present invention can also be applied to an ear hole type hearing aid such as a canal type, a concha type, and a CIC type.
- FIG. 14 it is assumed that the hearing aid wearer strikes or plays the vicinity of the front microphone 101F of the hearing aid 100 with the fingernail 911 in order to change the setting.
- FIG. 14A is a diagram showing the operation
- FIG. 14B is a diagram showing a time response in that case.
- FIG. 14 (a) shows that the ear-hook type hearing aid 100 is attached to the auricle 900 of the hearing aid wearer, and the setting change operation is performed with the finger 910.
- Two microphones are mounted on the hearing aid 100, and there are a front microphone 101F and a rear microphone 101R. Further, in order to incorporate (input) sound into each microphone, the front microphone 101F has a front sound hole 601F, and the rear microphone 101R has a rear sound hole 601R.
- FIG. 14B shows the time response 621F of the input signal of the front microphone 101F and the input signal of the rear microphone 101R when the vicinity of the front microphone 101F of the hearing aid 100 is hit or played with the fingernail 911.
- the time response 621F has a larger amplitude than the time response 621R.
- the hearing aid 100 can identify that the hearing aid wearer has contacted the vicinity of the front microphone 101F.
- FIG. 15 assumes that the hearing aid wearer strikes or plays the vicinity of the rear microphone 101R of the hearing aid 100 with the fingernail 911 in order to change the setting.
- FIG. 15A is a diagram showing the operation
- FIG. 15B is a diagram showing a time response in that case.
- FIG. 15B shows the time response 622F of the input signal of the front microphone 101F when the vicinity of the rear microphone 101R of the hearing aid 100 is hit or played with the fingernail 911, and the input of the rear microphone 101R.
- a time response 622R of the signal is shown.
- the time response 622R has a larger amplitude than the time response 622F.
- the front and rear microphone signal comparison unit 610 of the hearing aid 100 changes the hearing aid wearer's position. Operations can be identified. At this time, the front and rear microphone signal comparison unit 610 compares the amplitude values of the respective input signals indicated in the time response 621F and the time response 621R, and the setting control unit 126 determines the plurality of hearing aids 100 based on the amplitude. Identify and change settings. As a result, the intent of the hearing aid wearer can be identified by the hearing aid 100, and the setting can be changed as intended without causing the hearing aid wearer to feel uncomfortable.
- FIG. 16 it is assumed that the hearing aid wearer rubs or strokes the hearing aid 100 from the rear microphone 101R to the front microphone 101F with the fingernail 911 in order to change the setting.
- FIG. 16A shows the operation
- FIG. 16B shows the time response in that case.
- the description of the same part as in FIG. 14 (a) is omitted, but the different part is different from that of the rear microphone 101F with the fingernail 911, for example, for the hearing aid wearer to change the setting of the hearing aid 100. It is a point which rubs or strokes in the direction of the front side microphone 101F. That is, the operation here is an operation in which the fingernail 911 is brought into contact with the hearing aid 100 and the finger is moved in the direction of the arrow illustrated in FIG.
- FIG. 16B shows the time response 631F of the input signal of the front microphone 101F when the fingernail 911 rubs in the direction of the front microphone 101F from the rear microphone 101R of the hearing aid 100, and the rear side.
- the time response 631R of the input signal of the microphone 101R is shown.
- the hearing aid 100 can identify that the hearing aid wearer is an operation of rubbing or stroking the hearing aid 100 from the rear side to the front side.
- FIG. 17 it is assumed that the hearing aid wearer rubs or strokes the fingertip 911 in the direction from the front microphone 101F of the hearing aid 100 to the rear microphone 101R in order to change the setting.
- FIG. 17A is a diagram showing the operation
- FIG. 17B is a diagram showing a time response in that case.
- the description of the same part as in FIG. 16A is omitted, but the different part is different from the front microphone 101F, for example, with a fingernail 911 for the hearing aid wearer to change the setting of the hearing aid 100.
- the point is that it is rubbed or stroked in the direction of the rear microphone 101R. That is, the operation here is an operation in which the fingernail 911 is brought into contact with the hearing aid 100 and the finger is moved in the direction of the arrow shown in FIG.
- FIG. 17B shows the time response 632F of the input signal of the front microphone 101F when the fingertip 911 rubs in the direction from the front microphone 101F of the hearing aid 100 to the rear microphone 101R, or when stroked.
- the time response 632R of the input signal of the microphone 101R is shown.
- the hearing aid 100 can identify that the hearing aid wearer is rubbing or stroking the hearing aid 100 from the front side to the rear side.
- the front and rear microphone signal comparison unit 610 of the hearing aid 100 can identify the stroke operation. At this time, the front and rear microphone signal comparison unit 610 determines the time difference between the amplitude peak points of each input signal indicated in the time response 621F and the time response 621R, and the setting control unit 126 is based on the time difference between the amplitude peak points.
- a plurality of settings of the hearing aid 100 are identified and changed. As a result, the intent of the hearing aid wearer can be identified by the hearing aid 100, and the setting can be changed as intended without causing the hearing aid wearer to feel uncomfortable.
- a disk-shaped variable volume change switch may be used as a means for setting the volume, and this operation and the hearing aid of the present embodiment are rubbed, or The operation of stroking is similar. From this, it is possible to easily reduce erroneous operations on the volume setting of the hearing aid wearer by rubbing or stroking as an operation for increasing or decreasing the volume.
- the present invention is useful as a hearing aid, a hearing aid system, or the like that does not feel uncomfortable due to a change in the setting of the hearing aid and can further simplify the change of the setting.
- Control signal generation unit 6 Call detection unit 10
- Telephone 40 100 Hearing aid 41 Sound wave reception unit 43
- Power amplification unit 46
- Analysis control unit 101 Microphone 101F Front microphone 101R Rear microphone 103 Receiver 111 A / D conversion unit 118 Hearing aid signal processing unit 119 D / A conversion unit 120
- Signal processing unit 121 Signal intensity calculation unit 123
- Threshold storage unit 124
- Signal intensity comparison unit 125
- Setting control unit 201
- FFT unit 202 Spectrum comparison unit 400
- Hearing aid Setting device 401
- Setting selection unit 403 Maska sound storage unit 404
- Setting sound 420 Setting change signal processing unit 501
- Threshold storage unit 502 Maski sound extraction unit 503
- Signal Determination unit 601F front sound hole 601R rear sound hole 6 0
- Front / rear microphone signal comparison unit 621F Input signal from front microphone when hitting near
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Abstract
Description
図1は、本発明の第1の実施形態にかかる補聴器の概略構成の一例を示すブロック図である。図1に示す補聴器100は、入力音から入力信号を生成するマイク101と、入力信号をディジタル信号に変換するA/D変換部111と、入力信号を加工して出力信号を生成する信号処理部120と、入力信号としての音声信号の周波数特性等を調整する、つまり周波数特性等を制御する補聴器用信号処理部118と、ディジタル信号をアナログ信号に変換するD/A変換部119と、D/A変換されたアナログ信号である出力信号から出力音を再生するレシーバ103とを備える。
次に、本実施形態の補聴器への様々な接触音を入力した場合の時間応答について説明する。ここでは、補聴器として、耳掛型補聴器、小型耳掛型補聴器を用いている。ここでは、耳掛型補聴器とは、補聴器本体の全長(本体とは、ハンガー部分、チュブ部分を除く本体部分を指す)が略3cm以上であるものを指し、小型耳掛型補聴器とは、補聴器本体の全長が略3cm未満であるものを指している。
図3は、本発明の第2の実施形態にかかる補聴器システムの概略構成の一例を示すブロック図である。本実施形態の補聴器システムは、補聴器設定装置400と補聴器100とからなる。補聴器設定装置400は、補聴器の所定の設定が入力される設定選択部401と、マスカ音(マスクする音)を記憶するマスカ音記憶部403と、マスキ音(マスクされる音)を記憶するマスキ音記憶部404と、補聴器設定に基づいてマスカ音およびマスキ音から設定音を合成する設定音合成部405と、設定音をアナログ信号に変換するD/A変換部407と、設定音を出力するスピーカ408とを備える。なお、第1の実施形態にかかる補聴器の構成と同一の部分に関しては、同一の符号を付し、説明を省略または簡略化する。
なお、音源生成装置がマスカ音を生成する際に、マスカ音はマスキ音に含まれる周波数成分を含まない音源、つまり、マスキ音に含まれる周波数成分以外の周波数成分を含む音源を選択することが望ましい。また、音源生成装置が、マスカ音を生成する際、耳障りでない音、例えば音楽などを選択することにより、補聴器装用者の不快感を低減することができる。このように生成したマスカ音は、マスカ音記憶部403に記憶する。
本発明の第3の実施形態にかかる補聴器の目的は、補聴器装用者の設定変更回数の低減と、補聴器装用者の意図しない設定変更の防止である。例えば補聴器の音量の増減を設定する際に、例えば増加方向と減少方向で別設定が出来ず、巡回して音量設定が切り替る場合を考える。一例として、補聴器装用者の意図として音量減をしたいにも関わらず、巡回設定として一旦音量増加してから上限に到達した後に、音量の下限に切り替る場合が考えられる。この場合、補聴器装用者にとって複数回の設定変更が必要で、かつ意図せずに一時的に音量増設定になってしまい、不便に感じることがある。これに対して、補聴器装用者の操作の違いを補聴器で識別することにより、音量増なのか音量減なのかを識別して、1回の操作で意図通りの設定を反映する方法を説明する。
本出願は、2008年8月20日出願の日本特許出願No.2008-212050に基づくものであり、その内容はここに参照として取り込まれる。
5 制御信号発生部
6 通話検出部
10 電話機
40,100 補聴器
41 音波受信部
43 受信切換部
44 電力増幅部
46 分析制御部
101 マイク
101F 前側マイク
101R 後側マイク
103 レシーバ
111 A/D変換部
118 補聴器用信号処理部
119 D/A変換部
120 信号処理部
121 信号強度算出部
123 閾値記憶部
124 信号強度比較部
125 信号判定部
126 設定制御部
201 FFT部
202 スペクトル比較部
400 補聴器設定装置
401 設定選択部
403 マスカ音記憶部
404 マスキ音記憶部
405 設定音合成部
407 D/A変換部
408 スピーカ
410 設定音
420 設定変更用信号処理部
501 閾値記憶部
502 マスキ音抽出部
503 信号判定部
601F 前側音孔
601R 後側音孔
610 前後マイク信号比較部
621F 爪先で前側音孔付近を叩いた場合の前側マイクからの入力信号
621R 爪先で前側音孔付近を叩いた場合の後側マイクからの入力信号
622F 爪先で後側音孔付近を叩いた場合の前側マイクからの入力信号
622R 爪先で後側音孔付近を叩いた場合の後側マイクからの入力信号
631F 爪先で後側音孔から前側音孔の方向に擦った場合の前側マイクからの入力信号
631R 爪先で後側音孔から前側音孔の方向に擦った場合の後側マイクからの入力信号
632F 爪先で前側音孔から後側音孔の方向に擦った場合の前側マイクからの入力信号
632R 爪先で前側音孔から後側音孔の方向に擦った場合の後側マイクからの入力信号
900 耳介
910 指
911 指の爪先
Claims (19)
- 入力音から入力信号を生成するマイクと、
前記入力信号から出力信号を生成する信号処理部と、
前記出力信号から出力音を再生するレシーバと
を備え、
前記信号処理部は、所定時間区間において、当該補聴器への接触時に発生する接触音に基づく前記入力信号の時間応答を判定し、前記時間応答に基づいて当該補聴器の設定を変更する
補聴器。 - 請求項1に記載の補聴器であって、
前記信号処理部は、前記入力信号の強度を算出し、所定時間区間における前記入力信号の強度の平均値が第1の所定閾値以下であり、かつ、前記所定時間区間における前記入力信号の強度が第2の所定閾値以上になる時点を少なくとも2回検知することにより、当該補聴器の設定を変更する
補聴器。 - 請求項2に記載の補聴器であって、
前記信号処理部は、前記入力信号の強度が前記第2の所定閾値以上になる時点を検知するための時間幅を設定する
補聴器。 - 請求項3に記載の補聴器であって、
前記接触音は、爪先で弾く音または爪先のタップ音であり、
前記信号処理部は、前記時間幅を20msec以下に設定する
補聴器。 - 請求項3に記載の補聴器であって、
前記信号処理部は、前記入力信号の強度が前記第2の所定閾値以上になる時点を検知した時間幅に対して、前記信号強度を低減する
補聴器。 - 請求項1に記載の補聴器であって、
前記信号処理部は、前記入力信号の強度を算出し、所定時間区間における前記入力信号の強度の平均値が第1の所定閾値以下であり、かつ、前記入力信号を周波数領域の信号に変換し、前記周波数領域の信号の波形と所定信号の波形との差分が第3の所定閾値以下になる時点を少なくとも2回検知することにより、当該補聴器の設定を変更する
補聴器。 - 請求項6に記載の補聴器であって、
前記信号処理部は、前記周波数領域の信号の波形と所定信号の波形との差分が前記第3の所定閾値以下である時点を検知するための時間幅を設定する
補聴器。 - 請求項7に記載の補聴器であって、
前記接触音は、爪先で弾く音または爪先のタップ音であり、
前記信号処理部は、前記時間幅を20msec以下に設定する
補聴器。 - 請求項7に記載の補聴器であって、
前記信号処理部は、前記周波数領域の信号の波形と所定信号の波形との差分が前記第3の所定閾値以下である時点を検知した時間幅に対して、前記信号強度を低減する
補聴器。 - 請求項1ないし9のいずれか1項に記載の補聴器であって、
前記信号処理部は、当該補聴器の設定を変更した旨を報知する
補聴器。 - 補聴器と前記補聴器の設定を変更する補聴器設定装置とを有する補聴器システムであって、
前記補聴器設定装置は、
前記補聴器の設定を入力する入力部と、
前記補聴器の設定を変更する際に出力する調整音を示すマスキ音および前記マスキ音をマスクするためのマスカ音の情報を記憶する記憶部と、
前記記憶部に記憶された前記マスカ音および前記マスキ音と前記入力部により入力された前記補聴器の設定に基づいて、出力信号を生成する信号合成部と、
前記出力信号から設定音を再生するスピーカと、
を備え、
前記補聴器は、
前記補聴器設定装置により再生された設定音から設定信号を生成するマイクと、
前記設定信号から前記マスキ音を抽出し、抽出したマスキ音から前記補聴器の設定を抽出し、抽出した補聴器の設定に基づいて当該補聴器の設定を変更する信号処理部と、
を備える補聴器システム。 - 請求項11に記載の補聴器システムであって、
前記マスキ音を示す信号の信号強度は、前記マスカ音を示す信号の信号強度以下である
補聴器システム。 - 請求項11に記載の補聴器システムであって、
前記マスキ音は、純音である
補聴器システム。 - 請求項11ないし13のいずれか1項に記載の補聴器システムであって、
前記補聴器の前記信号処理部は、当該補聴器の設定を変更した旨を報知する
補聴器システム。 - 請求項11に記載の補聴器システムであって、
前記マスカ音は、前記マスキ音に含まれる周波数成分以外の周波数成分を含む
補聴器システム。 - 請求項1に記載の補聴器であって、
前記信号処理部は、前記入力信号の強度を算出し、所定時間区間における前記入力信号の強度の平均値が第1の所定閾値以下であり、かつ、前記所定時間区間における前記入力信号の強度が第2の所定閾値以上になる回数を検知し、前記回数に基づいて当該補聴器の複数の設定を識別して変更する
補聴器。 - 入力音から第1入力信号を生成する第1マイクと
入力音から第2入力信号を生成する第2マイクと、
前記第1入力信号と前記第2入力信号から出力信号を生成する信号処理部と、
前記出力信号から出力音を再生するレシーバと
を備え、
前記信号処理部は、所定時間区間において、当該補聴器への接触時に発生する接触音に基づく前記第1入力信号および前記第2入力信号の時間応答を判定し、前記時間応答に基づいて当該補聴器の複数の設定を識別して変更する
補聴器。 - 請求項17に記載の補聴器であって、
前記信号処理部は、前記第1入力信号と前記第2入力信号の振幅値を比較し、前記振幅値に基づいて、当該補聴器の複数の設定を識別して変更する
補聴器。 - 請求項17に記載の補聴器であって、
前記信号処理部は、前記第1入力信号と前記第2入力信号の振幅ピーク時点の時間差を判定し、前記振幅ピーク時点の時間差に基づいて、当該補聴器の複数の設定を識別して変更する
補聴器。
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US13/059,875 US8041063B2 (en) | 2008-08-20 | 2009-08-18 | Hearing aid and hearing aid system |
JP2010525593A JP4727763B2 (ja) | 2008-08-20 | 2009-08-18 | 補聴器および補聴器システム |
US13/232,030 US8488825B2 (en) | 2008-08-20 | 2011-09-14 | Hearing aid and hearing aid system |
Applications Claiming Priority (2)
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---|---|---|---|
JP2008212050 | 2008-08-20 | ||
JP2008-212050 | 2008-08-20 |
Related Child Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US13/059,875 A-371-Of-International US8041063B2 (en) | 2008-08-20 | 2009-08-18 | Hearing aid and hearing aid system |
US13/232,030 Division US8488825B2 (en) | 2008-08-20 | 2011-09-14 | Hearing aid and hearing aid system |
Publications (1)
Publication Number | Publication Date |
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WO2010021125A1 true WO2010021125A1 (ja) | 2010-02-25 |
Family
ID=41707016
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PCT/JP2009/003931 WO2010021125A1 (ja) | 2008-08-20 | 2009-08-18 | 補聴器および補聴器システム |
Country Status (3)
Country | Link |
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US (2) | US8041063B2 (ja) |
JP (1) | JP4727763B2 (ja) |
WO (1) | WO2010021125A1 (ja) |
Cited By (3)
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JP2012168499A (ja) * | 2011-01-28 | 2012-09-06 | Fujitsu Ltd | 音声補正装置、音声補正方法及び音声補正プログラム |
WO2012124776A1 (ja) * | 2011-03-17 | 2012-09-20 | シャープ株式会社 | 電子機器、電子機器の制御方法、制御プログラムおよび記録媒体 |
JP2012244582A (ja) * | 2011-05-24 | 2012-12-10 | Rion Co Ltd | 補聴器 |
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DE102009021855A1 (de) * | 2009-05-19 | 2010-11-25 | Siemens Medical Instruments Pte. Ltd. | Verfahren zur Akklimatisierung einer programmierbaren Hörvorrichtung und zugehörige Hörvorrichtung |
US8792661B2 (en) * | 2010-01-20 | 2014-07-29 | Audiotoniq, Inc. | Hearing aids, computing devices, and methods for hearing aid profile update |
KR20120002737A (ko) * | 2010-07-01 | 2012-01-09 | 삼성전자주식회사 | 마이크를 이용한 휴대용 단말기의 동작 제어 방법 및 장치 |
US8964509B2 (en) * | 2011-12-21 | 2015-02-24 | Utc Fire & Security Corporation | Remote communication and control of acoustic detectors |
KR101976091B1 (ko) * | 2013-01-24 | 2019-05-09 | 삼성전자주식회사 | 청각 기기의 동작 모드를 결정하는 방법 및 청각 기기 |
TWI544478B (zh) * | 2014-04-10 | 2016-08-01 | 拓集科技股份有限公司 | 基於聲音觸發之作業啟始方法及系統,及相關電腦程式產品 |
US11032656B2 (en) | 2017-06-06 | 2021-06-08 | Gn Hearing A/S | Audition of hearing device settings, associated system and hearing device |
WO2021236830A1 (en) | 2020-05-22 | 2021-11-25 | Team Ip Holdings, Llc | Face mask with audio device holder |
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Also Published As
Publication number | Publication date |
---|---|
US20120002829A1 (en) | 2012-01-05 |
JP4727763B2 (ja) | 2011-07-20 |
JPWO2010021125A1 (ja) | 2012-01-26 |
US20110142273A1 (en) | 2011-06-16 |
US8488825B2 (en) | 2013-07-16 |
US8041063B2 (en) | 2011-10-18 |
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