This application is related to the following commonly assigned U.S. patent applications which are herein incorporated by reference in their entirety: “Automatic Switch for Hearing Aid,” Ser. No. 09/659,214, filed on Sep. 11, 2000; “Diotic Presentation of Second-Order Gradient Directional Hearing Aid Signals,” Ser. No. 10/146,536, filed on May 15, 2002; and “Switching Structures For Hearing Aid,” Ser. No. 10/244,295, filed on Sep. 16, 2002.
This application relates generally to hearing aid systems and, more particularly, to systems, devices and methods for selectively coupling hearing aids to electromagnetic signals.
Some hearing aids provide adjustable operational modes or characteristics that improve the performance of the hearing aid for a specific person or in a specific environment. Some of the operational characteristics are on/off, volume control, tone control, and selective signal input. One way to control these characteristics is by a manually engagable switch on the hearing aid.
Some hearing aids include both a non-directional microphone and a directional microphone in a single hearing aid. When a person is talking to someone in a crowded room the hearing aid can be switched to the directional microphone in an attempt to directionally focus the reception of the hearing aid and prevent amplification of unwanted sounds from the surrounding environment. Some hearing aids include a manually-actuated switch. Actuation of these switches can be inconvenient and difficult, especially for those with impaired finger dexterity.
The volume for some hearing aids is adjusted using magnetically activated switches that are controlled by holding magnetic actuators adjacent to the hearing aids. Actuation of these switches can be inconvenient because a person is required to have the magnetic actuator available to change the volume.
With respect to telephone use, some hearing aids have an input which receives the electromagnetic voice signal directly from the voice coil of a telephone instead of receiving the acoustic signal emanating from the telephone speaker. Conventionally, a telephone handset provides an electromagnetic voice signal to only one ear. Thus, only a single hearing aid of a two hearing aid system is in use with a telephone handset. Moreover, the hearing aid that is not receiving the signal from the telephone handset continues to amplify signals from the surrounding environment that may interfere with the wearer's ability to hear the desired telephone signal.
There is a need in the art to provide improved systems, devices and methods for providing improved systems and methods for selectively coupling hearing aids to electromagnetic fields such as that produced by telephone coils.
The above mentioned problems are addressed by the present subject matter and will be understood by reading and studying the following specification. The present subject matter provides improved systems, devices and methods for selectively coupling hearing aids to electromagnetic signals. In various embodiments, the present subject matter provides improved coupling to electromagnetic signals from telephone receivers.
One aspect relates to a hearing aid device. In various embodiments, the hearing aid device includes an induction signal receiver for receiving induction signals, a microphone system for receiving acoustic signals, a hearing aid receiver, and a signal processing circuit operably connected to the induction signal receiver, the microphone system, and the hearing aid receiver. The signal processing circuit includes a proximity sensor, such as a magnetic sensor, for detecting an induction source, such as a telephone voice coil, for example. The signal processing circuit presents a first signal to the hearing aid receiver that is representative of the acoustic signals. When the induction source is detected, the signal processing circuit presents a second signal to the hearing aid receiver that is representative of the induction signals and transmits a third signal representative of the induction signals from the hearing aid device to a second hearing aid device.
In various embodiments, the hearing aid device includes an induction signal receiver for receiving induction signals, a microphone system for receiving acoustic signals, a hearing aid receiver, and a signal processing circuit operably connected to the induction signal receiver, the microphone system, and the hearing aid receiver. The signal processing circuit has an acoustic operational state to present a first signal to the hearing aid receiver that is representative of the acoustic signals, and an induction operational state to present a second signal to the hearing aid receiver that is representative of the induction signals. In the induction operational state, the signal processing circuit transmits a third signal representative of the induction signals from the hearing aid device to a second hearing aid device.
According to various embodiments, the hearing aid device forms a first hearing aid device in a system that also includes a second hearing aid device. The second hearing aid device includes a microphone system for receiving acoustic signals, a hearing aid receiver, and a signal processing circuit operably connected to the microphone system and the hearing aid receiver. The signal processing circuit of the second hearing aid device has an acoustic operational state to present a fourth signal to the hearing aid receiver that is representative of the acoustic signals, and an induction operational state to receive the transmitted third signal from the first hearing aid device representative of the induction signals. In the induction operational state, the signal processing circuit of the second hearing aid device presents a fifth signal to the hearing aid receiver that is representative of the induction signals.
One aspect relates to a method for selectively coupling a hearing aid system to induction signals produced by an induction source, such as a telephone voice coil, for example. In various embodiments, a first signal representative of acoustic signals is presented to a first hearing aid receiver in a first hearing aid device to assist with hearing in a first ear. An induction field source is detected. Upon the detection of the induction field source, a second signal representative of induction signals from the induction field source is presented to the first hearing aid receiver to assist hearing in the first ear, and a third signal representative of the induction signals is transmitted to a second hearing aid device to assist hearing in a second ear. According to various embodiments, the second signal and the third signal are used to diotically present acoustic representative of the induction signals to a wearer.
These and other aspects, embodiments, advantages, and features will become apparent from the following description and the referenced drawings.
The following detailed description of the present subject matter refers to the accompanying drawings which show, by way of illustration, specific aspects and embodiments in which the present subject matter may be practiced. In the drawings, like numerals describe substantially similar components throughout the several views. These embodiments are described in sufficient detail to enable those skilled in the art to practice the present subject matter. Other embodiments may be utilized and structural, logical, and electrical changes may be made without departing from the scope of the present subject matter. The following detailed description is, therefore, not to be taken in a limiting sense, and the scope of the present subject matter is defined only by the appended claims, along with the full scope of equivalents to which such claims are entitled.
The environment of the illustrated system 230 includes an induction source 234 and an acoustic source 235. One example of an induction source is a telephone voice coil such as that found in the telephone handset. Other examples of induction sources include, but are not limited to, inductive loop assistive listening systems such as a loop of wire around a room or around a wearer's neck The induction source 234 provides an induction signal 236 and a magnetic field gradient. The acoustic source 235 provides an acoustic signal 237.
In the illustrated embodiment, the first hearing aid device 231 includes a hearing aid receiver 238 (or speaker), a signal processing circuit 239, an microphone system 240, and induction signal receiver 241. According to various embodiments, the signal processing circuit 239 includes a proximity sensor such as a magnetic field sensor 242. The microphone system 240 is capable of detecting the acoustic signal 237 and providing a representative signal to the signal processing circuit 239. The induction signal receiver 241 is capable of detecting the induction signal 236 and providing a representative signal to the signal processing circuit 239. The sensor 242 detects when the first hearing aid is proximate to or within range of the induction source. In one embodiment, a magnetic field sensor 242 detects a magnetic field gradient 243 such as that produced by a permanent magnet 122 in a telephone handset, as illustrated in
In various embodiments, sensor 242 includes a reed switch. In various embodiments, sensor 242 includes a solid state switch. In various embodiments, solid state switch 242 includes a MAGFET. In various embodiments, the solid state switch 242 is a giant magneto resistive switch. In various embodiments, the solid state switch 242 is an anisotropic resistive switch. In various embodiments, the solid state switch 242 is a spin dependent tunneling switch. In various embodiments, the solid state switch 242 is a Hall Effect switch.
The signal processing circuit 239 provides various signal processing functions which, according to various embodiments, include noise reduction, amplification, frequency response, and/or tone control. In various embodiments, the signal processing circuit 239 includes an acoustic mode 244, an induction mode 245 and a transmitter (induction/TX) mode 246. These modes can be viewed as operational states. In various embodiments, the acoustic mode 244 is the default mode for the signal processing circuit 239. In the acoustic mode 244, the signal processing circuit 239 receives a signal from the microphone system 240 and presents a representative signal to the hearing aid receiver 238 to transmit acoustic signals into a wearer's ear. In the induction mode 245, the signal processing circuit 239 receives a signal from the induction signal receiver 241 and presents a representative signal to the hearing aid receiver 238 to transmit acoustic signals into a wearer's ear. In the induction/TX mode 246, the signal processing circuit 239 receives a signal from the induction signal receiver 241 and presents a representative signal to a wireless transmitter 247 to wirelessly transmit a representative signal to the second hearing aid device 232. In various embodiments, the induction mode 245 and the induction/TX mode 246 function together as a single operational state. As is explained in more detail below, the second hearing aid device receives the wirelessly transmitted signal such that a signal representative of the induction signal 236 is diotically presented to the wearer using the first and second hearing aid devices 231 and 232.
According to various embodiments, the magnetic field sensor 242 automatically switches the signal processing circuit 239 among the available modes of operation. In various embodiments, the magnetic field sensor 242 automatically switches the signal processing circuit 239 from an acoustic mode 244 to both the induction mode 245 and the induction/TX mode 239. In these embodiments, the induction mode 245 and the induction/TX mode 239 function together as a single mode which functions mutually exclusively with respect to the acoustic mode 244.
In the illustrated embodiment, the second hearing aid device 232 includes a hearing aid receiver 248 (or speaker), a signal processing circuit 249, a microphone system 250, and a wireless receiver 251. The microphone system 250 is capable of detecting the acoustic signal 237 and providing a representative signal to the signal processing circuit 249.
The signal processing circuit 249 provides various signal processing functions which, according to various embodiments, include noise reduction, amplification, frequency response shaping, and/or compression. In various embodiments, the signal processing circuit 249 includes an acoustic mode 252, and a receiver (induction/RX) mode 253. In various embodiments, the acoustic mode 252 is the default mode for the signal processing circuit 249. In the acoustic mode 252, the signal processing circuit 249 receives a signal from the microphone system 250 and presents a representative signal to the hearing aid receiver 248 to transmit acoustic signals into a wearer's ear. In the induction/RX mode 253, the signal processing circuit 249 receives wirelessly transmitted signal 233 from the first hearing aid device 231 via the wireless receiver 251 and presents a representative signal to the hearing aid receiver 248. Thus, the illustrated system 230 diotically presents a signal representative of the induction signal 236 to the wearer using the first and second hearing aid devices 231 and 232.
According to various embodiments, the signal processing circuit 249 automatically switches among the available modes of operation. In various embodiments, the signal processing circuit 249 automatically switches from the acoustic mode 252 to both the induction/RX mode 253 when signal 233 is present. In these embodiments, the induction/RX mode 253 function and acoustic mode 252 are mutually exclusive.
In various embodiments, the wireless transmitter 247 includes an RF transmitter and the wireless receiver 251 includes an RF receiver. In various embodiments, the wireless transmitter 247 includes a tuned circuit to transmit an inductively transmitted signal, and the wireless receiver 251 includes an amplitude modulated receiver to receive the inductively transmitted signal.
In the illustrated device 631, the sensor 642 provides a ground path, and thus selectively provides power, either to the microphone system 640 or to both the induction signal receiver 641 and the wireless transmitter 647. One of ordinary skill in the art will understand, upon reading and comprehending this disclosure, that various embodiments provide the sensor between the power rail and the components 641, 640 and 647 so as to selectively connect and disconnect power to the components (i.e. to selectively actuate and deactivate the components).
In various embodiments, the magnetic field sensor 642 defaults to provide power to the microphone system and does not provide power to the induction signal receiver 641 and the wireless transmitter 647. Thus, the signal processing circuit 639 receives a signal from the microphone system, and provides a representative signal to the hearing aid receiver 638. According to various embodiments, when the sensor 642 detects a magnetic field gradient from a telephone receiver, the sensor 642 provides power to the induction signal receiver 641 and the wireless transmitter 647, and does not provide power to the microphone system 640. Thus, the signal processing circuit 639 receives a signal from the induction signal receiver 641, provides a representative signal to the hearing aid receiver 638, and wirelessly transmits a representative signal using wireless transmitter 647.
In the illustrated device 832, a switch 860 in the signal processing circuit 849 provides a ground path, and thus selectively provides power, either to the microphone system 850 or to the wireless receiver 851. One of ordinary skill in the art will understand, upon reading and comprehending this disclosure, that various embodiments provide the sensor between the power rail and the components 850 and 851 so as to selectively connect and disconnect power to the components. In various embodiments, a wireless communication detector 861 detects a wireless communication from the first hearing aid device (not shown) and provides a control signal to the switch 860. In various embodiments, the wireless communication detector 861 forms part of the wireless receiver 851. In these embodiments, the detector 861 remains active regardless of whether power is generally provided to the receiver 851.
A switching circuit 940 is provided to switch the hearing aid input from the microphone 931, the default state, to the induction coil pickup 932, the magnetic field sensing state. It is desired to automatically switch the states of the hearing aid 910 when the telephone handset 914 is adjacent the hearing aid wearer's ear. Thereby, the need for the wearer to manually switch the input state of the hearing aid when answering a telephone call and after the call ends. Finding and changing the state of the switch on a miniaturized hearing aid can be difficult especially when the wearer is under the time constraints of a ringing telephone or if the hearing aid is an in the ear type hearing aid. Additionally, older people tend to lose dexterity, and have great difficulty in feeling the small switch.
In this default, open state of switch 1055, switches 1051 and 1052 are conducting. Therefore, switch 1051 completes the circuit connecting microphone 1031 to the signal processing circuit 1034. Switch 1052 connects resistor 1059 to ground and draws the voltage away from the base of switch 1053 so that switch 1053 is open and not conducting. Accordingly, the hearing aid is operating with microphone 1031 active and the induction coil pickup 1032 inactive. The hearing aid inputs 1031, 1032 are thus mutually exclusive.
Switch 1055 is closed in the presence of a magnetic field, particularly in the presence of the magnetic field produced by telephone handset magnet 1022. In one embodiment of the present subject matter, switch 1055 is a reed switch, for example a microminiature reed switch, type HSR-003 manufactured by Hermetic Switch, Inc. of Chickasha, Okla. Another example of a micro reed switch is MMS-BV50273 manufactured by Meder Electronics of Mashpea, Mass. In a further embodiment of the present subject matter, the switch 1055 is a solid state, wirelessly operable switch. In various embodiments, wirelessly refers to a magnetic signal. Various embodiments of a magnetic signal operable switch is a MAGFET. The MAGFET is non-conducting in a magnetic field that is not strong enough to turn on the device and is conducting in a magnetic field of sufficient strength to turn on the MAGFET. In a further embodiment, switch 1055 is a micro-electro-mechanical system (MEMS) switch. In a further embodiment, the switch 1055 is a magneto resistive device that has a large resistance in the absence of a magnetic field and has a very small resistance in the presence of a magnetic field. When the telephone handset magnet 1022 is close enough to the hearing aid wearer's ear, the magnetic field produced by magnet 1022 changes the state of switch (e.g., closes) switch 1055. Consequently, the base of switch 1051 and the base of switch 1052 are now grounded. Switches 1051 and 1052 stop conducting and microphone ground is no longer grounded. That is, the microphone circuit is open. Now switch 1052 no longer draws the current away from the base of switch 1053 and same is energized by the hearing aid voltage source through resistor 1059. Switch 1053 is now conducting. Switch 1053 connects the voice pickup coil ground to ground and completes the circuit including the induction coil pickup 1032 and signal processing circuit 1034. Accordingly, the switching circuit 1040 activates either the microphone (default) input 1031 or the voice coil (magnetic field selected) input 1032 but not both inputs simultaneously.
In operation, switch 1055 automatically closes and conducts when it is in the presence of the magnetic field produced by telephone handset magnet 1022. This eliminates the need for the hearing aid wearer to find the switch, manually change switch state, and then answer the telephone. The wearer can conveniently, merely pickup the telephone handset and place it by his\her ear whereby hearing aid 10 automatically switches from receiving microphone (acoustic) input to receiving pickup coil (electromagnetic) input. That is, a static electromagnetic field causes the hearing aid to switch from an acoustic input to a time-varying electromagnetic field input. Additionally, hearing aid 1010 automatically switches back to microphone input after the telephone handset 1014 is removed from the ear. This is not only advantageous when the telephone conversation is complete but also when the wearer needs to talk with someone present (microphone input) and then return to talk with the person on the phone (voice coil input).
While the disclosed embodiment references an in-the-ear hearing aid, it will be recognized that the inventive features of the present subject matter are adaptable to other styles of hearing assistance devices, including over-the-ear, behind-the-ear, eye glass mount, implants, body worn aids, noise protection earphones, headphones, etc. Due to the miniaturization of hearing aids, the present subject matter is advantageous to many miniaturized hearing aids. Hearing aids as used herein refer to any device that aids a person's hearings, for example, devices that amplify sound, devices that attenuate sound, and devices that deliver sound to a specific person such as headsets for portable music players or radios.
NPN transistors are generally illustrated as switches in
In various embodiments, the first input 1371 is a microphone system. According to various embodiments, the microphone system includes an omnidirectional microphone system, a directional microphone system or a microphone system capable of switching between an omnidirectional and a direction microphone system. Omnidirectional microphone systems detect acoustical signals in a broad pattern. Directional microphone systems detect acoustical signals in a narrow pattern. In various embodiments, the microphone system (first input) provides a default input to the hearing aid.
In various embodiments, the second input 1372 is an induction signal receiver. When the switching circuit 1340 senses the magnetic field, the hearing aid 1370 switches from its default mode to receive signals from the induction signal receiver (second input 1372). In various embodiments, the activation of the second input 1372 is mutually exclusive of activation of the first input 1371.
In use with a telephone handset, e.g., 114 shown in
In various embodiment, switching circuit 1340 includes a micro-electromechanical system (MEMS) switch. In various embodiments, the MEMS switch includes a cantilevered arm that in a first position completes an electrical connection and in a second position opens the electrical connection. When used in the circuit as shown in
The second hearing aid 1402 includes a first input 1471B. The first input 1471B is an acoustic input, e.g., microphone. A switching circuit 1440B determines whether input 1471B is electrically connected to the signal processing circuit 1434B. The signal processing circuit 1434B performs any of a number of operations on the signal the input 1471B and outputs a conditioned signal, which is tuned to the specific hearing assistance needs of the wearer, to the output speaker 1436B. The second hearing aid 1402 assists a wearer's hearing in an ear different from the first. Often times, an individual in need of a hearing assistance device has different hearing assistance needs in each ear. Accordingly, the signal processor 1434B of the second hearing aid 1402 conditions a hearing signal differently then the first hearing aid's signal processor 1434A.
Wireless connection 1403 includes a transmitter 1405 connected to the first hearing aid 1401 and a receiver 1407 connected to the second hearing aid 1402. In various embodiments, receiver 1407 includes an amplitude modulated transmitter circuit such as a Ferranti MK-484 solid state AM receiver. In various embodiments, other wireless technology is incorporated. In various embodiments, the receiver 1407 is positioned within the housing (ear mold) of the second hearing aid and is powered by the second hearing aid battery (not shown). Transmitter 1405, in various embodiments, includes a tuned circuit that produces an amplitude modulated signal that is adapted for reception by the receiver 1407. In various embodiments, the transmitter 1405 is positioned within the housing (ear mold) of the first hearing aid and is powered by the first hearing aid battery (not shown). The transmitter 1405 is connected to the first hearing aid switching circuit 1440A and based on the state of switching circuit 1440B, transmitter 1405 sends a signal to the receiver 1407. In various embodiments, the receiver 1407 sends a signal to switching circuit 1440B. In response to this signal, the switching circuit 1440B turns off the first input 1471B. Additionally, in response to this signal, the switching circuit 1440B sends a signal to the signal processing circuit to process a signal received at receiver 1407 that is representative of a signal provided by the second input 1472A of the first hearing aid 1401. Thus, for example, the transmitter 1405 sends a second hearing aid microphone 1471B off signal to the receiver 1407. The second hearing aid microphone 1471B is off while the first hearing aid 1401 is in a state with the second input 1472A being active. Accordingly, the wearer of the hearing aid system 1400 receives a signal only from the second input 1472A of the first hearing aid 1401 in the first ear. No input into the second ear is received from the first input (microphone) 1471B of the second hearing aid 1402.
The transmitter 1405 sends the second state signal of the first hearing aid 1401 to the second hearing aid 1402. The second hearing aid 1402 turns off input 1471B based on the signal received by receiver 1407. In various embodiments, the transmitter 1405 receives a processed signal from the signal processing circuit 1434A and sends the processed signal to the receiver 1407. In various embodiments, the transmitter 1405 receives the input signal from the second input 1472A and sends this signal to the receiver 1407. The receiver 1407 provides the received signal to the signal processor of 1434B of the second hearing aid 1402. The signal processor 1434B processes the signal to the hearing assistance needs of the second ear and sends a conditioned signal to output speaker 1436B. Accordingly, the wearer of the hearing aid system 1400 receives conditioned signals based on inductive signals sensed by the second input 1472A of the first hearing aid 1401 from both the first hearing aid 1401 and the second hearing aid 1402. That is, the input, for example, telecoil input from a telephone, into one hearing aid is provided to the hearing aid wearer in both ears. Such a diotic signal utilizes both signal processing abilities of both hearing aids 1401, 1402 to provide a signal to the wearer that improves performance. When the second hearing aid 1402 is an in-the-ear or behind-the-ear hearing aid, the body (ear mold) of the second hearing aid passively attenuates ambient noise. It is noted that the present subject matter is not limited to a particular hearing aid type, as it can be incorporated with in-the ear hearing aids, behind-the-ear hearing aids, in-the-canal hearing aids, completely in the canal (CIC) hearing aids, and other hearing aid devices. Moreover, the first and second hearing aids 1401, 1402 both providing a diotic signal (which is conditioned for a respective ear) to the wearer. The diotic signal allows both hearing aids to use less gain due to central fusion summing of the signal.
The first hearing aid 1501 includes a first transceiver 1506A that is connected to the switching circuit 1540A and the signal processing circuit 1534A. The transceiver 1506A receives a state signal from the switching circuit 1540A. The state signal represents which of the two inputs 1571A, 1572A is currently actively sensing an input signal. In various embodiments, the first input is the default state of the hearing aid 1501. The first input 1571A includes a microphone that senses and transduces an acoustic signal into an electrical signal. In various embodiments, the second input 1572A includes an induction sensor, e.g., a telecoil. The second input 1571A senses a magnetic field and transduces the magnetic signal into an electrical signal.
The second hearing aid 1502 includes a second transceiver 1506B that is connected to the switching circuit 1540B and the signal processing circuit 1534B. The second transceiver 1506B receives a state signal from the switching circuit 1540B. The state signal represents which of the two inputs 1571B, 1572B is currently actively sensing an input signal and sending an electrical signal to the signal processing circuit 1534B. In various embodiments, the first input is the default state of the second hearing aid 1502. The first input 1571B includes a microphone that senses and transduces an acoustic signal into an electrical signal. In various embodiments, the second input 1572B of the second hearing aid 1506B includes an induction sensor, e.g., a telecoil. The second input 1572B senses a magnetic field and transduces the magnetic signal into an electrical signal.
The default state of the system 1500 includes both the first inputs 1571A and 1571B sending signals to the respective signal processing circuits 1534A and 1534B. Thus, the wearer of the hearing aid system 1500 receives a binaural signal representative of the acoustics of the surrounding environment.
Wireless connection 1503 links the first and second hearing aids 1501, 1502 through transceivers 1506A, 1506B. The first transceiver 1506A and the second transceiver 1506B stand ready to receive a signal from the other transceiver with both the first and second hearing aids operating in the default mode. The default mode for both hearing aids 1501, 1502 includes the first inputs 1571A and 1571B being active and acoustically sensing a signal. The hearing aids 1501, 1502 respectively condition signals sensed by inputs 1571A, 1571B, respectively for output to the respective ears of the wearer. When the switching circuit 1540A changes the mode of the hearing aid 1501 from the first input 1571A to the second input 1572A, the first transceiver 1506A sends a signal to the second transceiver 1506B. The second transceiver 1506B causes the second switching circuit 1540B to turn off the first input 1571B and the second input 1572B (the second hearing aid signal is provided by the second input 1571A of the second hearing aid 1501 and is received by the signal processing circuit 1534B). Thus, the first input 1571B and the second input 1572B are turned off when the first hearing aid 1501 is in its second input mode with its second input 1572A sensing an input signal and providing same to the signal processing circuit 1534A.
In various embodiments, the transceivers communicate a processed signal from one of the signal processing circuits to the other; and in various embodiments, the transceivers communicate an unprocessed signal from one of the signal processing circuits to the other transceiver. For example, in various embodiments, the first transceiver 1506A receives the second state, input signal from the second input 1572A. The first transceiver 1506A sends this input signal to the second transceiver 1506B. Thus, the second hearing aid 1502 receives the unprocessed output signal from the second input 1572A of the first hearing aid 1501. The second transceiver 1506B sends the received signal to the signal processing circuit 1534B. Signal processing circuit 1534B processes the signal and sends a further processed signal, which is processed to produce an output signal that matches the hearing assistance needs of the second ear, to the output speaker 1536B. Accordingly, both the first and second hearing aids 1501, 1502 respectively output to the first and second ears a signal based on the input sensed by the second input 1572A of the first hearing aid 1501. In one use, the second input 1572A includes a telecoil that senses the time-varying component of a telephone handset. As a result, the hearing aid system wearer receives the telephone input in both ears by wirelessly linking the first hearing aid to the second hearing aid.
The second transceiver 1506B receives a state signal from the switch 1540B and sends this signal to the first transceiver 1506A in the second input mode of the second hearing aid 1502. The first transceiver 1506A provides this signal to the switching circuit 1540A, which turns off the first input 1571A and the second input 1572A. Thus, the first input 1571A and the second input 1572A are off when the second input 1571B of the second hearing aid 1502 is active (the first hearing aid signal is provided by the second input 1571B of the second hearing aid 1502 and is received by the signal processing circuit 1534A). In various embodiments, the second transceiver 1506B receives the second state, input signal from the second input 1572B. The second transceiver 1506B sends this input signal to the first transceiver 1506A. Thus, the first hearing aid 1501 receives the unprocessed output signal from the second input 1572B of the second hearing aid 1502. The first transceiver 1506A sends the received signal to the signal processing circuit 1534A of the first hearing aid 1501. Signal processing circuit 1534A processes the signal and sends a further processed signal, which is processed to produce an output signal that matches the hearing assistance needs of the first ear, to the output speaker 1536A. Accordingly, both the first and second hearing aids 1501, 1502 respectively output to the first and second ears a signal based on the input sensed by the second input 1572B of the second hearing aid 1502. In one use, the second input 1572B includes a telecoil that senses the time-varying component of a telephone handset. As a result, the hearing aid system wearer receives the telephone input in both ears by wirelessly linking the first hearing aid 1501 to the second hearing aid 1502. Further, the hearing aid system wearer is not limited to inductive input to only one hearing aid. The wearer uses either hearing aid to provide inductive input to both hearing aids and thus, both ears. In various embodiments, the transceivers communicate a processed signal from one of the signal processing circuits to the other; and in various embodiments, the transceivers communicate an unprocessed signal from one of the signal processing circuits to the other transceiver. For example, in various embodiments, the second transceiver 1506B receives the signal from the signal processing circuit 1534B and sends this signal to the first transceiver 1506A in the second input mode of the second hearing aid 1502. Thus, the first hearing aid 1501 receives the unprocessed output signal from the second hearing aid 1502. The first transceiver 1506A sends the received signal to the signal processing circuit 1534A of the first hearing aid 1501. Signal processing circuit 1534A processes the signal and sends a further processed signal, which is processed to produce an output signal that matches the hearing assistance needs of the first ear, to the output speaker 1536A of the first hearing aid. Accordingly, both the first and second hearing aids 1501, 1502 respectively output to the first and second ears a signal based on the input sensed by the second input 1572B of the second hearing aid 1502. In one use, the second input 1572B includes a telecoil that senses the time-varying component of a telephone handset. As a result, the hearing aid system wearer receives the telephone input in both ears by wirelessly linking the first hearing aid 1501 to the second hearing aid 1502.
Wireless connection 1603 includes transmitter circuit block 1605 that is adapted to send a wireless signal to receiver 1607. Transmitter circuit block 1605 is connected to the receiver 1611A through a magnetical field operable switch 1617. Switch 1617 completes the electrical circuit and causes the transmitter circuit block 1605 to transmit a signal when the switch is closed. The normal, default state of the switch 1617 is open. The switch 1617 closes when it senses a magnetic field of sufficient strength to close the switch and/or cause the switch to conduct. Switch 1617, in various embodiments, is a mechanical switch. In various embodiments, mechanical switch 1617 is a reed switch. In various embodiments, switch 1617 is a solid state switch. In various embodiments, solid state switch 1617 is a MAGFET. In various embodiments, the solid state switch 1617 is a giant magneto resistive switch. In various embodiments, the solid state switch 1617 is a anisotropic resistive switch. In various embodiments, the solid state switch 1617 is a spin dependent tunneling switch. The switch 1617 is set to conduct when the switch 1613A switches the input circuit 1610A to telecoil input 1672A. In various embodiments, the transmitter circuit block 1605 connects one of the telecoil input 1672A or the input to the receiver 1611A to the transmitter circuit block 1605. The electrical connections for the embodiment with the transmitter circuit block 1605 connected directly to the telecoil input are shown in broken line in
Second hearing aid 1602 includes elements that are substantially similar to elements in first hearing aid 1601. These elements are designated by the same numbers with the suffix changed to “B”. Receiver 1607 is adapted to receive a signal from transmitter circuit block 1605. A master switch 1613B connects the receiver to the second input circuit 1610B. Master switch 1613B, in various embodiments, is a manual switch that allows the hearing aid wearer to turn of the receiver block 1607 and, hence, the wireless connection 1603. The receiver 1607 is also connected to the telecoil input 1672B of the second hearing aid 1602. In various embodiments, the master switch 1613 is a switch that selects the active input, either the microphone input 1671B or the telecoil input 1672B. In operation, when the receiver 1607 detects a signal from transmitter 1605, the master switch 1613B switches from its default state with the microphone input 1671B selected to the telecoil input 1672B selected (telecoil input state). The telecoil input 1672B is not hard wired to a telecoil. The telecoil input 1672B receives an input signal from receiver 1607. This input signal is from the telecoil input 1672A connected to the other hearing aid 1601 and is wirelessly broadcast by the transmitter circuit block 1605 to receiver 1607. Accordingly, the hearing aid system wearer receives a diotic signal from both hearing aids based on a single input received by a single hearing aid.
While the above described embodiments refer to a wireless link between the hearing aids, it will be recognized that the hearing aids could be hard wired together. However, consumers tend to prefer cosmetically attractive hearing aids, which are generally defined as smaller, less visible hearing aids.
The above description further uses an output speaker as the means to transmit an output signal to a hearing aid wearer. It will be recognized that other embodiments of the present subject matter include bone conductors and direct signal interfaces that provide the output signal to the hearing aid wearer.
As has been provided above, the present subject matter provides improved systems, devices and methods for selectively coupling hearing aids to electromagnetic fields. In various embodiments, a first hearing aid device is capable of operating in an acoustic mode to receive and process acoustic or acoustic signals, an electromagnetic mode to receive and process electromagnetic signals from a telephone coil when the telephone coil is proximate to the first hearing aid device, and an induction/transmitter mode to transmit a signal indicative of the received electromagnetic signals to a second hearing aid device. The second hearing aid device is capable of operating in an acoustic mode to receive and process acoustic or acoustic signals, and an induction/receiver mode to receive and process the signal transmitted from the first hearing aid device when a telephone coil is proximate to the first hearing aid device.
According to various embodiments, when a wearer places a telephone handset proximate to a hearing aid device, the hearing aid device is switched automatically into induction mode with a magnetic sensor (such as a reed switch or MEMS equivalent, for example), and the desired telephone signal is presented diotically to the two ears of the hearing aid wearer. The present subject matter improves listening over the telephone due to the amplification of the telephone signal in the remote ear and the passive attenuation of ambient sounds by the ear mold in that ear. According to various embodiments, less gain is required from each hearing aid due to central fusion summing the signals at the two ears.
One of ordinary skill in the art will understand, upon reading and comprehending this disclosure, that the present subject matter is capable of being incorporated in a variety of hearing aids. For example, the present subject mater is capable of being used in custom hearing aids such as in-the-ear, half-shell and in-the-canal styles of hearing aids, as well as for behind-the-ear hearing aids. Furthermore, one of ordinary skill in the art will understand, upon reading and comprehending this disclosure, the method aspects of the present subject matter using the figures presented and described in detail above.
Although specific embodiments have been illustrated and described herein, it will be appreciated by those of ordinary skill in the art that any arrangement which is calculated to achieve the same purpose may be substituted for the specific embodiment shown. This application is intended to cover adaptations or variations of the present subject matter. It is to be understood that the above description is intended to be illustrative, and not restrictive. Combinations of the above embodiments, and other embodiments will be apparent to those of skill in the art upon reviewing the above description. The scope of the present subject matter should be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled.
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