CN104853302B - Hearing aid configuration detection - Google Patents
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- CN104853302B CN104853302B CN201510086528.XA CN201510086528A CN104853302B CN 104853302 B CN104853302 B CN 104853302B CN 201510086528 A CN201510086528 A CN 201510086528A CN 104853302 B CN104853302 B CN 104853302B
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Abstract
A hearing aid comprising: a first housing that houses a first circuit; a second housing that houses a second circuit; and a connector configured for interconnection of the first circuit with the second circuit; wherein the connector includes a line for transmitting a first signal between the first circuit and the second circuit; wherein the second circuit comprises a transmitter configured to transmit a second signal having configuration information to the first circuit using the line; and wherein the first signal does not contain configuration information.
Description
Technical Field
The present disclosure relates to a new method for providing configuration information of a hearing aid, a hearing aid adapted to perform the method, and a system for fitting a hearing aid utilizing the configuration information.
Background
BTE (behind the ear) hearing aids are well known in the art. BTE hearing aids have a BTE housing shaped to be worn behind the pinna of a user. The BTE housing houses components for hearing loss compensation. A sound signal transmission member (i.e. a sound tube or an electrical conductor) transmits a signal representing the hearing loss compensating sound from the BTE housing into the ear canal of the user.
The output transducer may be a receiver arranged in the ear canal of the hearing aid user, a so-called in-the-ear receiver. A hearing aid with an in-the-ear receiver will be referred to as RIE hearing aid in the following.
In RIE hearing aids, the sound signal transmission part comprises an electrical conductor for propagating a hearing loss compensated audio sound signal from the hearing aid circuitry in the BTE hearing aid housing through the conductor to a receiver arranged in the ear canal of the user for emitting sound towards the eardrum of the user.
In order to provide a safe and comfortable positioning of the receiver in the ear canal of the user, an in-ear shell, an earpiece, an earplug or an earmould may be provided for insertion into the ear canal of the user.
The terms in-ear shell, earpiece, earplug and earmould are used interchangeably below.
Typically, hearing aid manufacturers provide a number of different earphones with receivers having different output power specifications, e.g. five different output power levels.
Typically, the headset is also provided with sound signal transmission members of different lengths, for example eight different lengths, to suit the individual physiological structure of the intended user.
Thus, for example, 8 x 5-40 different earphones may be used together with a particular BTE housing.
Furthermore, in order to conform to the user's ear and to ensure that the sound signal transmission parts and other components are in their intended position in the ear canal, and to prevent the earpiece from falling out of the ear, e.g. when the user moves the jaw, the earpiece, earplug or earmould may be individually customized, or may also be manufactured in a number of standard sizes, which further increases the number of earpieces that can be used with a particular BTE housing.
The headset may further house one or more microphones, for example a microphone for suppressing occlusion effects and/or one or more microphones for recording directional cues, which further increases the number of headsets that may be used with a particular BTE housing.
This results in a wide variety of headsets that can be used with a particular BTE housing.
Disclosure of Invention
Thus, by providing a smaller number of different combinations of different sub-assemblies, a wide variety of hearing aids may be provided. Therefore, there is a need to automatically detect the actual configuration of each hearing aid.
Thus, a new hearing aid is provided with:
a first housing that houses a first circuit;
a second housing that houses a second circuit; and
a connector configured for interconnection of the first circuit with the second circuit, having
Circuitry for transmitting a first signal between the first circuit and the second circuit; and wherein
The second circuit comprises a transmitter configured to transmit a second signal having configuration information to the first circuit using the line; and wherein
The first signal does not include the configuration information.
The new hearing aid may be configured for adjusting its operation in accordance with the configuration information.
The second circuit with the transmitter may be configured for transmitting the second signal with the configuration information to the first circuit when the hearing aid is powered up, and/or when the hearing aid receives a user request from a user interface of the hearing aid for transmitting the second signal, and/or when the hearing aid receives a request from an external device, such as a fitting instrument, for transmitting the second signal.
There is also provided a new method of identifying a component, or a combination of components connected to a circuit with a connector, comprising transmitting configuration information regarding the identity of the component, the combination of components, on a line coupled to the connector and providing transmission of other information than the configuration information.
A new method of hearing aid configuration, comprising:
interconnecting the first circuit with the second circuit using a connector having lines configured to transmit the first signal;
transmitting a second signal containing configuration information related to a second circuit to the first circuit on the line, wherein
The first signal does not contain configuration information.
A new fitting instrument for a hearing aid is also provided, which is configured for receiving configuration information.
The newly installed instrument may be configured for installing the hearing aid according to the configuration information.
The newly installed instrument may be configured to display a message in response to the configuration information.
The newly installed instrument may be a dedicated instrument, or a PC, handheld device, e.g. tablet, smart phone, etc. with suitable installation software, with a suitable APP, etc.
By automatic identification of the component or combination of components, e.g. a receiver in an earpiece, a misadjustment of the hearing aid in question is avoided.
For example, during initial installation of the hearing aid to the intended user, a faster and safer initial installation may be performed by the dispenser due to automatic identification of the component(s) (e.g. receiver type), e.g. left and right in-ear shells may be automatically detected for negligence exchange. It also relieves the distributor of the task of manually entering configuration information during installation and avoids incorrect gain calibration and output levels due to incorrect manually entered component information.
Furthermore, a disadjustment of the hearing aid due to inadvertent undesired combination of components, such as an inadvertent interconnection of the wrong in-ear housing and the BTE housing, is avoided. For example, the start-up procedure of the hearing aid may be stopped when an undesired combination of components is detected, and/or certain functions of the hearing aid may be implemented only when a combination of components suitable for performing the function is detected.
Furthermore, it is easy for the hearing aid in question to identify the correct replacement part number.
Furthermore, the user of the hearing aid may be warned about incorrect component combinations, for example when the left and right ear components are inadvertently exchanged, for example when an in-ear housing intended for the right ear is inadvertently connected to a BTE housing mounted for the left ear. Furthermore, if the wrong replacement part is inadvertently delivered to the user and used with the hearing aid, the user may be alerted, thereby reducing the annoyance of the user and the possible additional access to the office of the distributor.
Automatic identification is provided without increasing the number of conductors interconnecting the first circuit with the second circuit, since the lines for transmitting configuration information are already provided for other purposes. In this way, existing hearing aid parts can be configured to perform the new method without modification of the hardware, such as modification of the connector. Furthermore, the complexity and cost of the connector is kept to a minimum.
The first signal may be an audio signal representing sound, for example an audio signal transmitted to a receiver for emitting sound towards the eardrum of a user.
The second circuit may include a power supply. The power source may be powered by a wire. For example, the power supply can be charged on the line by transmitting a high frequency signal f >20 kHz. The power supply may be a capacitor.
The second circuit may comprise a receiver. The line may be an input line of the receiver.
The transmitter may be configured for transmitting the signal by means of at least one varying signal parameter, such as amplitude, frequency, phase, pulse width, etc.
The transmitter may be configured for modulation of the line, such as by amplitude modulation, frequency modulation, phase modulation, and so forth.
The transmitter may be configured for digital modulation of the line, for example by phase shift keying, frequency shift keying, amplitude shift keying, quadrature amplitude modulation, and so on.
The configuration information may include information identifying a particular arrangement of parts or components interconnected by the first and/or second circuits.
In particular, the configuration information may include an identifier of a component and/or a combination of components of the second circuit.
The configuration information may include an identifier of a combination of components of the second circuit.
The type of hearing aid and the mounting parameters may depend primarily on the components or combination of components of the second circuit.
It is therefore important for a particular user to provide the correct combination of the first and second circuits of the hearing aid and the fitting parameters of the hearing aid.
A wrong combination may lead to a serious maladjustment of the hearing aid.
The transmitter may be configured to transmit the configuration information through the short-circuit line. A short circuit may result in a corresponding voltage drop of the battery supply voltage, which may be detected and decoded by the first circuit (e.g. by a signal processor of the first circuit, e.g. a signal processor configured for hearing loss compensation), thereby identifying one component or a combination of components of the second circuit in the first circuit.
The first housing may be a behind-the-ear housing and the second housing may be an earphone.
The second circuit may include a microcontroller programmed to short the line according to a coded time sequence for identifying one component or combination of components of the second circuit.
RIE hearing aids may be provided with connectors to facilitate connection and disconnection of the second circuitry of the second housing (such as an earphone) to the first circuitry of the first housing (such as a BTE housing). In this way, for example, it is easy to connect various types of receivers in the earpiece to the BTE housing, thereby providing different receivers for different hearing aids.
The newly installed instrument may automatically respond to the received configuration information, for example by selecting hearing aid parameters based on the received configuration information (e.g. the identified specific model of the receiver). In this way, the receiver, hearing aid and hearing aid fitting parameters are correctly combined.
The operator of the newly installed instrument may take appropriate action in response to the display of the configuration information, for example by adjusting hearing aid parameters according to the configuration information (e.g. the specific model of the identified receiver). In this way, the receiver, hearing aid and hearing aid fitting parameters are correctly combined.
The operator of the newly installed instrument may take appropriate action in response to the display of the configuration information, for example by replacing the receiver (in case it is not possible to tune the hearing aid to the specific model of the identified receiver). In this way, undesired combinations of receiver, hearing aid and hearing aid fitting parameters may be discovered and corrected.
The hearing aid and the adjustment of the hearing aid parameters may be controlled internally by the hearing aid.
Throughout this disclosure, "audio signal" may be used to identify any analog or digital signal forming part of a signal path from an input to an output of a hearing aid.
The signal processing in the new hearing aid as well as in the new mounted instrument may be performed by dedicated hardware, may also be performed in a signal processor, or in a combination of dedicated hardware and one or more signal processors.
As used herein, the terms "processor," "signal processor," "controller," "system," and the like are intended to refer to a CPU-related entity, either hardware, a combination of hardware and software, or software in execution.
For example, a "processor," "signal processor," "controller," "system," and the like may be, but are not limited to being, a process running on a processor, an object, an executable, a thread of execution, and/or a program.
By way of illustration, the terms "processor," "signal processor," "controller," "system," and the like designate both an application running on a processor and a hardware processor. One or more "processors," "signal processors," "controllers," "systems," and the like, or any combination thereof, may reside within a process and/or thread of execution, and one or more "processors," "signal processors," "controllers," "systems," and the like, or any combination thereof, may be localized on one hardware processor, possibly combined with other hardware circuitry, and/or distributed between two or more hardware processors, possibly combined with other hardware circuitry.
Further, a processor (or similar term) may be any component or any combination of components capable of performing signal processing. For example, the signal processor may be an ASIC processor, an FPGA processor, a general purpose processor, a microprocessor, a circuit component, or an integrated circuit.
A hearing aid comprising: a first housing that houses a first circuit; a second housing that houses a second circuit; and a connector configured for interconnection of the first circuit with the second circuit; wherein the connector comprises circuitry for transmitting a first signal between the first circuit and the second circuit; wherein the second circuit comprises a transmitter configured to transmit a second signal having configuration information to the first circuit using the line; and wherein the first signal does not contain the configuration information.
Optionally, the first signal is an audio signal representing sound.
Optionally, the second circuit comprises a power supply which is charged by a third signal transmitted on the line.
Optionally, the second circuit comprises a receiver.
Optionally, the line is an input line of the receiver.
Optionally, the transmitter is configured for transmitting the second signal by at least one varying signal parameter selected from the group comprising amplitude, frequency, phase and pulse width.
Optionally, the second signal is modulated, and wherein the modulation is selected from the group consisting of amplitude modulation, frequency modulation, and phase modulation.
Optionally, the second signal is digitally modulated, and wherein the digital modulation is selected from the group consisting of phase shift keying, frequency shift keying, amplitude shift keying, and quadrature amplitude modulation.
Optionally, the transmitter is configured to transmit the second signal by short-circuiting the line.
Optionally, the configuration information comprises an identifier of one or more components in the second circuit.
Optionally, the configuration information comprises a plurality of identifiers of respective components in the second circuit.
Optionally, the first housing is a behind-the-ear housing and the second housing is an in-the-ear housing.
A fitting instrument for a hearing aid configured to receive said configuration information.
Optionally, the fitting instrument is configured for fitting the hearing aid based on the configuration information.
Optionally, the installation apparatus is configured to display a message in response to the configuration information.
A method of configuring a hearing aid having a connector interconnecting a first circuit of the hearing aid with a second circuit of the hearing aid, the connector having a line configured to transmit a first signal between the first circuit and the second circuit, the method comprising: transmitting a second signal to the first circuit using the line, the second signal containing configuration information relating to the second circuit; wherein the first signal does not include the configuration information.
Other and further aspects and features will be apparent from a reading of the following detailed description of the embodiments.
Drawings
The new method, the hearing aid and the fitting instrument will be described in more detail below with reference to the accompanying drawings, in which various examples are shown. In the drawings:
fig. 1 schematically illustrates an exemplary new hearing aid;
fig. 2 shows a perspective view of a new RIE type of hearing aid; and
fig. 3 shows a hearing aid circuit for automatic configuration detection.
Detailed Description
The new method, hearing aid and fitting instrument will be described more fully below with reference to the accompanying drawings, in which various examples of the new method, hearing aid and fitting instrument are shown. However, the new method, hearing aid and fitting instrument may be embodied in different forms and should not be construed as being limited to the examples set forth herein.
It should also be noted that the figures are only intended to help describe the embodiments. They are not intended as an exhaustive description of the invention nor as a limitation on the scope of the invention. Moreover, the illustrated embodiments need not have all of the aspects or advantages shown. A solution or advantage described in connection with a particular embodiment is not necessarily limited to that embodiment, but may be implemented in any other embodiment, even if not so shown, or not so explicitly described.
Like reference numerals refer to like elements throughout. Therefore, the description with respect to each drawing does not describe the same elements in detail.
Fig. 1 to 3, in particular fig. 1, schematically show a BIE hearing aid 10 to be worn behind a pinna 100 of a user, comprising a first housing, i.e. a BTE hearing aid housing (not shown — the outer wall is removed so that the inner parts are visible). The BTE housing houses a first circuit 12, the first circuit 12 having at least one BTE sound input transducer 14, 16 (i.e., a front microphone 14 and a rear microphone 16) for converting acoustic sound signals into respective microphone audio sound signals, an optional pre-filter (not shown) for filtering the respective microphone audio sound signals, an a/D converter (not shown) for converting the microphone audio sound signals into respective digital microphone audio sound signals, the respective digital microphone audio sound signals being input to a processor 18, the processor 18 being configured to generate a hearing loss compensation output signal based on the input digital audio sound signals.
The hearing loss compensated output signal is transmitted via a line 44 (not visible) with wires contained in the sound signal transmission member 20 to the receiver 22 of the second circuit 24 housed in a second housing (not shown-the outer wall is removed so that the internal parts are visible). The receiver 22 provides an acoustic output signal based on the hearing loss compensated output signal for transmission to the eardrum of the user. The second housing constitutes an earpiece 62, the outer shape of the earpiece 62 being configured to be comfortably placed in the ear canal of a user for securing and holding the receiver 22 and the sound signal transmission member 20 in their intended positions in the ear canal of the user as is well known in the art of BTE hearing aids.
The earpiece 62 with the sound transmission member 20 is connected to the BTE housing with the connector 30, the connector 30 facilitating the connection and removal of the earpiece 62.
The earpiece 62 comprises the sound transmission member 20. A number of different headsets may be connected to the BTE housing with the connector 30, such as headsets housing:
a) one receiver and zero microphones;
b) one microphone and zero receivers;
c) a receiver and a microphone positioned for directional cues;
d) one receiver and zero microphones positioned to suppress occlusions;
e) one receiver and two microphones (directional cues and occlusion), etc.
The above-described earphone may further include receivers having different power levels (e.g., four different levels), and may further include the sound tube part 20 having different lengths (e.g., five different standard lengths).
Further, a headset configured for a left ear and a headset configured for a right ear are provided.
Furthermore, some headsets may be provided with other sensors, such as temperature sensors, pressure sensors, orientation sensors, and the like.
Therefore, a wide variety of earphones can be easily provided; and thus automatic detection of the headset actually connected to the BTE housing with the connector 30 is very advantageous, e.g. to avoid errors.
The earpiece 62 shown in the figure houses an in-the-ear (ITE) microphone 26, the ITE microphone 26 being placed at the entrance of the ear canal when the earpiece 62 is placed in its intended position in the ear canal of the user. The ITE microphone 26 is connected to an a/D converter (not shown) and optionally to a pre-filter (not shown) in the BTE housing, with interconnecting wires (not visible) contained in the sound transmission part 20.
The BTE hearing aid 10 is powered by a battery 28. The battery 28 may be rechargeable.
In use, the ITE microphone 26 is placed at the entrance of the ear canal of the user. In this position, the output signal of the ITE microphone (hereinafter referred to as an ITE audio sound signal, generated by the ITE microphone 26 in response to acoustic sounds received by the ITE microphone 26) preserves spatial cues of the received acoustic sound signal; or in other words, the ITE microphone 26 is positioned such that its transfer function constitutes a good approximation of the head-related transfer function of the user.
The processor 18 passes the directional information contained in the ITE audio sound signal to the hearing loss compensated output signal (thereby also preserving spatial cues) so that the user maintains his or her positioning ability.
The ITE microphone 26 is operated close to the receiver 22 so that the risk of feedback is high, which limits the maximum stabilization gain available through the hearing aid 10.
However, in the hearing aid 10, the output signals of the microphones 14, 16 and the ITE microphone 26 are subjected to signal processing, e.g. adaptive filtering as described in more detail in european patent application No.:12199761.3, thus preserving and conveying spatial cues to the user of the hearing aid while suppressing feedback.
As described above, in order to suppress occlusion, the microphone may be housed in the second housing, that is, the earphone 62. When the earpiece 62 is placed in its intended position in the ear canal of the user, the microphone is placed inside the ear canal, close to the eardrum.
Often, occlusion of the ear canal due to the second housing (earpiece) results in a change in the user's perception of the user's own voice.
Sound originating from the vocal tract (throat and mouth) is transmitted into the ear canal through the cartilaginous tissue between these cavities and the outer part of the ear canal.
Most of this dominant low frequency sound simply escapes from the ear canal when nothing is placed in the ear canal. However, when the ear canal is blocked, these bone-conducted sounds cannot escape from the ear canal. The result is a high sound pressure level built up in the remaining ear canal volume. This increase in low frequency sound pressure is audible and can cause them to hear their own voice as loud and roaring. Sensing changes in own voice is the most prominent occlusion-related complaint, but not the only one. Other occlusion related problems include excessive low frequency amplification, decreased speech intelligibility, poor positioning, physical discomfort and increased risk of outer ear irritation and infection for hearing aid users with good low frequency hearing. The hearing aid user does not adapt to the occlusion and the occlusion effect is listed as a cause of dissatisfaction with their hearing aid by up to 27% of hearing aid wearers. This highlights the need to mitigate and even further eliminate the effects of occlusions.
As explained in more detail in EP 2434780 a1, in the ear canal of the user when the earpiece is placed in its intended position, the receiver may compensate for body conducted sounds based on the output signal of the microphone located close to the eardrum, so that the user perceives only hearing loss compensation signals, thereby suppressing occlusion effects.
Fig. 2 shows the new hearing aid 10 in its working position with the BTE housing 60 behind the user's ear (i.e. behind the pinna 100). As shown, the new hearing aid 10 may have a flexible arm 64 and is intended to be placed inside the pinna 100, e.g., around the outer ear behind the tragus and antitragus, abutting the antihelix, and at least partially covered by the antihelix to hold the earpiece 62 in its intended position inside the outer ear of the user. The arms may be preformed during manufacture, preferably in the form of an arch, with a curvature slightly greater than that of the antihelix, facilitating mounting of the arms in their intended position in the pinna 100.
Fig. 2 also schematically illustrates the new mounted instrument 70 and its wireless interconnection to the internet 200 and the new BTE hearing aid 10, the new BTE hearing aid 10 being shown in its working position with the BTE housing 60 behind the user's ear (i.e. behind the pinna 100).
The configuration information may be transmitted to the mounting instrument 70 by wireless means 80, for example displayed on a display of the mounting instrument 70 for confirmation by an operator of the mounting instrument 70 and possible corrective action in case the detected type of headset is not of the desired type.
The fitting instrument 70 is configured for fitting the hearing aid 10 according to the configuration information.
The fitting instrument 70 has a processor 72, the processor 72 being configured to be responsive to configuration information received from the hearing aid 10.
The fitting instrument may be configured to access a remote server via the internet 200, e.g. to access a database of further information about the hearing aid 10, e.g. based on received configuration information, e.g. via new values of a new type of fitting parameters for the earpiece 62.
Fig. 3 shows a block diagram of the hearing aid circuit 12, 24 for automatic configuration detection. In fig. 3, the second circuit 24 is housed in a second housing, i.e. in the headset 62; however, in another example, the second circuit 24 may be housed in the connector 30.
The second circuit 24 comprises a receiver 22 and a transmitter 40 in the form of a microcontroller 40, the microcontroller 40 being configured for transmission of a code uniquely identifying the type of headset 62 with the second circuit 24, e.g. the transmitted code contains configuration information, e.g. the power level of the receiver 22, whether the headset 62 is for the left or the right ear, and possibly the length of the sound transmission member 20, and possibly the number and type of microphones 26 (occlusion and/or spatial cues), and possibly the number and type of other sensors, etc.
The receiver 22 is driven by a receiver driver 42 housed in the first housing (i.e., the BTE housing 60). During normal operation of the hearing aid 10, the receiver driver 42 transmits a hearing loss compensating sound signal to the receiver on line 44 in the sound transmission member 20.
During start-up of the hearing aid 10, the receiver driver 42 transmits a high frequency signal on line 44, preferably at a frequency above 20 kHz. The high frequency signal charges the capacitor 46 through the diode 48 and during transmission of the code on line 44, the charged capacitor 46 then provides power to the transmitter (microcontroller) 40.
Further, the high frequency signal is low pass filtered in a low pass filter 50 and input to a microcontroller 40 configured to detect the presence of the high frequency signal. In addition, the microcontroller 40 is configured to transmit code on line 44 when capturing the high frequency signal.
The microcontroller 40 is configured to transmit a code over the intermittent short-circuit line 4, thereby creating a series of voltage drops in the supply voltage of the circuit in the BTE housing, which voltage drops are detected by the comparator 52 (already present with the voltage supply for monitoring the circuit) of the first circuit 12 in the BTE housing 60.
Thus, the code is transmitted to the receiver (always present in the hearing aid) and decoded using the signal line for transmitting the audio signal, and no circuitry needs to be added in the BTE housing.
The second circuit 24 may be configured to repeatedly transmit configuration information until power from the power source (e.g., the charged capacitor 46) of the second circuit is no longer available, or the second circuit 24 may be configured to repeatedly transmit configuration information until an acknowledgement signal is received from the first circuit, e.g., by transmitting a high frequency signal for a predetermined period of time, that the configuration information was successfully received.
While particular embodiments have been shown and described, it will be understood that they are not intended to limit the claimed invention, and it will be obvious to those skilled in the art that various changes and modifications may be made without departing from the spirit and scope of the claimed invention. The specification and drawings are, accordingly, to be regarded in an illustrative rather than a restrictive sense. The invention as claimed is intended to cover alternatives, modifications and equivalents as defined by the appended claims.
Claims (20)
1. A hearing aid comprising:
a first housing that houses a first circuit;
a second housing that houses a second circuit; and
a connector configured for interconnection of the first circuit with the second circuit;
wherein the connector comprises a line for transmitting a first signal between the first circuit and the second circuit;
wherein the second circuit comprises a transmitter configured to transmit a second signal with configuration information about the second circuit to the first circuit using the line; and
wherein the first signal does not contain the configuration information; and is
The transmitter is configured for transmitting the second signal with the configuration information by short-circuiting the line, causing a corresponding voltage drop of a supply voltage of the first circuit, the corresponding voltage drop being detected and decoded by the first circuit.
2. The hearing aid according to claim 1, wherein the hearing aid is configured to adapt its operation according to the configuration information.
3. The hearing aid according to claim 1, wherein the second circuit is configured for transmitting the second signal when the hearing aid is powered up.
4. The hearing aid according to claim 1, wherein the second circuit is configured for transmitting the second signal upon receiving a user request for transmission of the second signal from a user interface of the hearing aid.
5. The hearing aid according to claim 1, wherein the second circuit is configured to transmit the second signal upon receiving a request from an external device for transmission of the second signal.
6. A hearing aid according to claim 1, wherein the first signal is an audio signal representing sound.
7. The hearing aid according to claim 1, wherein the second circuit comprises a power supply which is charged with a third signal transmitted on the line.
8. The hearing aid according to claim 7, wherein the power supply is charged by transmitting a high frequency signal with a frequency higher than 20kHz on the line.
9. The hearing aid of claim 1, wherein the second circuit comprises a receiver.
10. A hearing aid according to claim 9, wherein the line is an input line of the receiver.
11. The hearing aid according to claim 1, wherein the transmitter is configured for transmitting the second signal with at least one varying signal parameter selected from the group comprising amplitude, frequency, phase and pulse width.
12. The hearing aid according to claim 1, wherein the second signal is modulated, and wherein the modulation is selected from the group comprising amplitude modulation, frequency modulation and phase modulation.
13. The hearing aid according to claim 1, wherein the second signal is digitally modulated, and wherein the digital modulation is selected from the group comprising phase shift keying, frequency shift keying, amplitude shift keying and quadrature amplitude modulation.
14. The hearing aid according to claim 1, wherein the second circuit has a microcontroller programmed to short-circuit the line according to a coded time sequence for identifying one component or a combination of components of the second circuit.
15. The hearing aid of claim 1, wherein the second circuit is configured to repeatedly transmit the configuration information until power from a power source of the second circuit is no longer available.
16. The hearing aid according to claim 1, wherein the second circuit is configured to repeat the transmission of the configuration information until receiving an acknowledgement signal from the first circuit that the configuration information has been successfully received.
17. The hearing aid of claim 1, wherein the configuration information comprises an identifier of one or more components in the second circuit.
18. The hearing aid of claim 1, wherein the configuration information comprises a plurality of identifiers for individual components in the second circuit.
19. The hearing aid according to claim 1, wherein the first housing is a behind-the-ear housing and the second housing is an in-the-ear housing.
20. A method of configuring a hearing aid having a connector interconnecting a first circuit of the hearing aid with a second circuit of the hearing aid, the connector having a line configured to transmit a first signal between the first circuit and the second circuit, the method comprising:
transmitting a second signal to the first circuit using the line, the second signal containing configuration information relating to the second circuit;
wherein the first signal does not contain the configuration information; and is
The transmitter of the second circuit transmits the second signal with the configuration information by short-circuiting the line, causing a corresponding voltage drop of the supply voltage of the first circuit, which voltage drop is detected and decoded by the first circuit.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DKPA201470077 | 2014-02-17 | ||
| DKPA201470077A DK201470077A1 (en) | 2014-02-17 | 2014-02-17 | Hearing aid configuration detection |
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| CN104853302A CN104853302A (en) | 2015-08-19 |
| CN104853302B true CN104853302B (en) | 2021-02-02 |
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| CN201510086528.XA Active CN104853302B (en) | 2014-02-17 | 2015-02-17 | Hearing aid configuration detection |
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| JP (2) | JP6903393B2 (en) |
| CN (1) | CN104853302B (en) |
| DK (1) | DK201470077A1 (en) |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| ITUB20155835A1 (en) * | 2015-11-24 | 2017-05-24 | St Microelectronics Srl | CIRCUIT OF DIAGNOSIS TO DETECT THE STATE OF LOADING OF AN AUDIO AMPLIFIER, CORRESPONDING AUDIO SYSTEM, INTEGRATED CIRCUIT AND PROCEDURE |
| CN106921925A (en) * | 2017-03-22 | 2017-07-04 | 杭州索菲康医疗器械有限公司 | A kind of hearing aid gain acquisition analysis system |
| EP3707919B1 (en) * | 2017-08-31 | 2023-06-21 | Sonova AG | A hearing device adapted to perform a self-test and a method for testing a hearing device |
| CN107864443B (en) * | 2017-10-30 | 2020-05-12 | 歌尔股份有限公司 | Earphone battery open circuit detection device and detection method |
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| CN101743762A (en) * | 2007-07-10 | 2010-06-16 | 唯听助听器公司 | Method for identifying a receiver in a hearing aid |
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| JP2862552B2 (en) * | 1989-02-15 | 1999-03-03 | 能美防災株式会社 | Fire alarm system |
| EP0480097B1 (en) * | 1990-10-12 | 1994-12-21 | Siemens Audiologische Technik GmbH | Hearing-aid with data memory |
| EP1133897B1 (en) * | 1998-11-24 | 2007-09-12 | Phonak Ag | Hearing aid |
| DE60307329T2 (en) * | 2003-03-19 | 2006-12-28 | Widex A/S | METHOD FOR PROGRAMMING A HEARING DEVICE BY MEANS OF A PROGRAMMING DEVICE |
| US20100208906A1 (en) * | 2007-07-26 | 2010-08-19 | Phonak Ag | Resistance identification of a peripheral unit on a hearing aid |
| EP2061274A1 (en) * | 2007-11-19 | 2009-05-20 | Oticon A/S | Hearing instrument using receivers with different performance characteristics |
| US20090179789A1 (en) * | 2008-01-14 | 2009-07-16 | Apple Inc. | Electronic device control based on user gestures applied to a media headset |
| WO2011110218A1 (en) * | 2010-03-09 | 2011-09-15 | Widex A/S | Two part hearing aid with databus and method of communicating between the parts |
| EP2661909B1 (en) * | 2011-01-07 | 2018-11-07 | Widex A/S | A hearing aid system with a dual mode wireless radio |
| EP2637423A1 (en) * | 2012-03-06 | 2013-09-11 | Oticon A/S | A test device for a speaker module for a listening device |
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Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101743762A (en) * | 2007-07-10 | 2010-06-16 | 唯听助听器公司 | Method for identifying a receiver in a hearing aid |
| CN101415140A (en) * | 2007-08-21 | 2009-04-22 | 西门子测听技术有限责任公司 | Automatic identification of receiver type in hearing aid devices |
| DE102008030551A1 (en) * | 2008-06-27 | 2009-08-27 | Siemens Medical Instruments Pte. Ltd. | Hearing device i.e. receiver-in-canal-behind-the-Ear hearing device, has identification unit digitally reading identification coding stored in identification memory of microphone module and hearing unit |
Also Published As
| Publication number | Publication date |
|---|---|
| JP2019216438A (en) | 2019-12-19 |
| JP6903393B2 (en) | 2021-07-14 |
| DK201470077A1 (en) | 2015-08-31 |
| JP2015164296A (en) | 2015-09-10 |
| CN104853302A (en) | 2015-08-19 |
| JP6963591B2 (en) | 2021-11-10 |
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