EP0823829A2 - Digital hearing aid system - Google Patents
Digital hearing aid system Download PDFInfo
- Publication number
- EP0823829A2 EP0823829A2 EP97305981A EP97305981A EP0823829A2 EP 0823829 A2 EP0823829 A2 EP 0823829A2 EP 97305981 A EP97305981 A EP 97305981A EP 97305981 A EP97305981 A EP 97305981A EP 0823829 A2 EP0823829 A2 EP 0823829A2
- Authority
- EP
- European Patent Office
- Prior art keywords
- digital
- aid
- processor
- hearing aid
- signal
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Withdrawn
Links
Images
Classifications
-
- 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
-
- 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
- H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
- H04R25/554—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired using a wireless connection, e.g. between microphone and amplifier or using Tcoils
-
- 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
- H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
- H04R25/558—Remote control, e.g. of amplification, frequency
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
- H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
- H04R2225/51—Aspects of antennas or their circuitry in or for hearing aids
-
- 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
- H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
- H04R25/552—Binaural
Definitions
- the invention pertains to electronic hearing aids. More particularly, the invention pertains to hearing aids which incorporate digital signal processors for processing and amplifying incident acoustic waves as well as equipment for programming such hearing aids.
- circuitry for the purpose of processing and amplifying an incident acoustic wave.
- the nature of the processing and the degree of amplification that is appropriate varies widely from one individual to another.
- an input transducer which converts an incident audio wave to an electrical signal is combined with an analog-to-digital converter, a digital signal processor, a control unit coupled to the digital signal processor and an output transducer which carries out a low-pass filter function simultaneously with generating an audible output wave.
- the digital signal processor incorporates a low-pass digital filter in combination with a high-pass digital filter.
- the filters include one or more programmable corner frequencies.
- a sigma-delta analog-to-digital converter is coupled between the input transducer and the digital signal processor.
- a decimation circuit can be coupled between the output of the converter and inputs to the signal paths of the dual digital filters.
- gain control can be accomplished in the signal path by multiplying a digital multi-bit gain control signal by a one or two bit representation of the digitized input signal, where there is no decimation circuitry.
- multiplication can be by a three to four bit representation of the digital input signal in the case of a circuit which carries out a decimation function by a factor of 2.
- the digital filters can be operated at high oversampling rates and can provide adjustable characteristic frequencies determined by filter coefficients which are binary based.
- filter coefficients which are binary based.
- the use of binary based filter coefficients eliminates any need for multipliers.
- Multiplication can be carried out by using shift operations. These could be implemented using multiplexer circuits for variable multiplications and hard wired offsets for fixed multiplications.
- the output digital-to-analog converter can be implemented without needing any additional filters beyond the low - pass characteristic of the output transducer.
- signal amplitudes which have been digitized can be converted to logarithmic form.
- additions and subtractions replace multiplications and divisions.
- Multiplication steps can be used to approximate exponential functions.
- circuit simplicity is promoted by use of a piecewise linear approximation to a logarithmic function. After processing, the resulting signals are converted back to a linear domain using a piecewise linear approximation to an exponential function.
- the hearing aid can include a programmable processor wherein control instructions can be stored in nonvolatile instruction memory when the unit is manufactured. This allows units to be built with different sets of instructions implementing different signal processing algorithms.
- one or more interfaces can be provided to enable the control unit to communicate with external circuitry.
- the interface can be directly coupled to an external programming apparatus for the purpose of reading out the values of parameters stored within the hearing aid and for adjusting parameters.
- a remote control unit can be provided. Such a unit could transmit a modulated RF carrier which could be detected by the interface of the hearing aid. Such an arrangement would make it possible to remotely control parameters of the aid so as to optimize performance thereof in view of the individual characteristics of a user and of the specific listening situation.
- the remote control unit can be coupled with a computer for the purpose of adjusting each of a number of sets of parameters stored within the remote control unit.
- a digital hearing aid in accordance with another aspect of the invention incorporates a sigma-delta A/D converter with either no decimation or with decimation by a factor of 2. This reduces substantially the amount of digital signal processing needed for decimation filtering.
- Gain control can be accomplished by multiplying a digital multibit gain control signal by a 1 or 2 bit representation of the digital input signal (in the case of no decimation) or by a 3 or 4 bit representation of the digital input signal (in the case of decimation by a factor of 2). This reduces substantially the complexity of the multiplier.
- IIR infinite impulse response
- a digital hearing aid embodying yet another aspect of the invention uses a digitally rectified, filtered, and decimated version of the output signal in each frequency band to represent the signal amplitude in that band. Digital implementation of these functions is accurate and efficient and requires no off-chip components. Decimation to a low sampling rate allows the control path to operate at a much reduced computation rate.
- Converting signal amplitude to a logarithmic domain using a piecewise linear approximation to a logarithmic function and then, after processing these signals using a control algorithm, converting the resulting control signals back to the linear domain using a piecewise linear approximation to an exponential function reduces hardware requirements. Multiplications and divisions are replaced by additions and subtractions and exponentials are replaced by rudimentary multiplications, greatly reducing circuit complexity. Also, the logarithmic domain expresses a wide dynamic range very efficiently. This allows providing enough capability to provide a dual input compression system, a dual output compression system, and a noise reduction system, with each of these independently adjustable for each of two frequency bands.
- a control processor that concurrently performs the operations of selection of two input operands, multiplication or shift, addition or subtraction or conditional selection, and output storage allows more processing per cycle than consecutive operation.
- a hearing aid with a digital serial interface in accordance with the present invention can use pulse width modulation (return-to-zero coding) for the transmitted data.
- pulse width modulation return-to-zero coding
- the transmitted signal is self clocking so that a separate clock line is not needed and timing is not critical. Also, since only a single signal line is used, it is readily adaptable to wireless communication.
- a hearing aid with a serial interface that includes an antenna switch and a carrier modulator so that the same tuned coil can be used as both a receive and transmit antenna. This permits wireless transmission in both directions, eliminating the need for a programming connector.
- a single tuned coil antenna saves cost and space. 50kHz pulse width modulation transfers a binary bit stream.
- a remote control for a hearing aid that embodies the present invention can use pulse width modulation of a 50kHz induction field (RF) carrier for data transmission.
- the carrier frequency is well beyond the audio band to minimize audible interference, but still below allocated frequencies.
- the induction field is not subject to body shadow effects and allows control of both hearing aids in a binaural fitting from the same remote control location. Pulse modulation allows highly efficient output stage.
- a remote control for a hearing aid that embodies the present invention can use two transmitting coils in space quadrature, driven with carriers in phase quadrature. This minimizes nulls in the pickup pattern of the transmitted signal.
- a remote control for a hearing aid can use a conditioning pulse and a transmitted identification number to signal a valid transmission for the hearing aid being controlled. This minimizes false actuation or actuation by another user and permits independent control of both hearing aids of a binaural pair.
- a remote control that uses tuned coils driven by a bridge type output in a switching mode provides high transmitter efficiency.
- a remote control having a programming connector enables a computer to program multiple memories in the remote control and that also enables a computer to program memories in the hearing aid using wireless transmission from the remote control to the hearing aid.
- wireless programming of the hearing aid can be effected using the modulator and transmitter already existing in the remote control.
- a hearing aid with a remote control that uses the same induction coil for receiving the remote control signal and for telephone induction pickup and induction loop pick up has reduced space requirements and cost.
- This remote control uses the same low frequency RF transmission for both the phone and remote control scheme. Both uses the same coil in and out.
- a hearing aid for use with this remote control uses AGC acting on the tuned receiver coil to control the sensitivity for the remote control signal while not affecting sensitivity for audio frequency induction signals. This reduces audible interference from the remote control.
- a computer interface permits programming hearing aids or remote controls that uses a computer parallel port to supply power for the interface and to provide bidirectional communication. This eliminates the size, cost, and inconvenience of a separate power supply.
- the computer software is able to control the signal switching pattern.
- Such a computer interface makes it possible to program hearing aids or remote controls by use of a transformer to transmit power to the interface and optocouplers to transmit signals to and from the interface. This provides electrical isolation needed to meet safety requirements.
- a hearing aid embodying the present invention can incorporate a signal-processing algorithm in which numerous parameters are field programmable over selected ranges in each of two channels. These include: Full-on Gain: 48 dB range in 3 dB increments. Corner Frequency: 500, 707, 1000, 1414, 2000, 2828, or 4000 Hz. Phase: In phase or out of phase. Primary Output AGC System
- the following parameters may be programmed at the time of hearing aid manufacture over various ranges in each of two channels.
- a fitting system can be provided that uses a fitting algorithm to select hearing aid parameters based on the factors of abnormal growth of loudness, widening of critical bands, abnormal upward spread of masking, and binaural vs. monaural fitting.
- a digital hearing aid system 10 of Fig. 1 contains digital hearing aids 12, 14 (binaural fitting) or a single digital hearing aid 12 or 14 (monaural fitting) worn by the user.
- the hearing aids 12, 14 are optionally equipped with programming sockets 12a, 14a to allow the hearing aid characteristics to be programmed for the individual user.
- a remote control unit 16 is carried by the user to control the operation of the hearing aid(s) 12, 14.
- the unit 16 is capable of transmitting, via radiant electromagnetic energy R, user-selected commands and parameter sets to the hearing aid(s) 12, 14 to adjust the hearing aids characteristics for various listening environments.
- the remote control unit 16 is equipped with a programming socket 16a to allow entering and storing of a number of user-selectable programs or parameter values.
- a programming interface 18 is coupled to a personal computer 18a.
- Programming cords and plugs 18b, 18c transmit the electrical signals needed to program the hearing aid(s) 12, 14 and remote control unit 16.
- the hearing aids 12, 14 are equipped with a wireless transmitter 18d and receiver 18e.
- the hearing aids 12, 14 can thus be remotely programmed or controlled.
- pickup 18e' can detect previously stored programs or data being read back to receiver 18e.
- a fitting program 18f can be run on the personal computer 18a to accept audiological data for the user, to determine the appropriate characteristics of the hearing aid(s) 12, 14 for that user, and to provide the appropriate data to the programming interface 18.
- the fitting program 18f can also provide other functions, such as storage and retrieval of user - specific data.
- the hearing aid system 10 may be provided in various forms.
- the hearing aid(s) 12, 14 may be behind-the-ear (BTE), in-the-ear (ITE), or in - the-canal type.
- the system 10 may be configured without the remote control unit 16, using a limited set of hearing aid mounted controls instead.
- the system 10 may even be configured with no user operated control other than an on/off switch.
- Fig. 2 illustrates a block diagram for a hearing aid such as the aid(s) 12, 14.
- the digital hearing aid(s) 12, 14 of Fig. 2 each contain a microphone 20 to receive acoustic signals in the audio frequency band.
- An inductive pickup coil 22 serves multiple a dual purposes.
- the coil 22 receives magnetic field signals in the audio frequency band from a telephone receiver or a transmitting induction loop. It can also receive remote control signals encoded on a transmitted or radiated electromagnetic carrier whose frequency is above the audio band. It can also be used to receive programming signals from transmitter 18d or to transmit programs or information to receiver 18e. For a hearing aid without an induction pickup option and without remote control and wireless options, the induction coil 22 is not needed.
- the connector 12a can optionally be provided for bidirectional transfer of encoded programming signals. Transfer can be in serial or parallel.
- An electronic signal processor 24 receives the above signals together with control signals from optional hearing aid mounted controls 26 and provides an electrical output signal at an output port 24a.
- a receiver 28 converts this electrical output signal to an acoustic output signal.
- a battery provides power for the electronic signal processor 24.
- the electronic signal processor 24 is illustrated in block diagram form in Fig. 3. The following table further explains the nature of the signals S1 to S21 shown in Figure 3.
- the processor 24 contains an induction coil preamplifier 22a to amplify the audio frequency signals and the remote control signals detected by the induction coil 22.
- Automatic gain control is included to control the output level of the remote control signal.
- a remote control signal detector 22b is coupled to the preamplifier 22a to recover the modulating signal from the carrier signal detected by coil 22.
- a preamplifier 20a is provided to amplify the signal from the microphone 20 and/or the output signal from the induction coil preamplifier 22a.
- AGC limiting is included to prevent overloading by high input signal levels.
- An analog-to-digital converter 30 is provided to convert the analog output of the preamplifier 20a to a digital form.
- the A/D converter 30 is based on sigma-delta modulation of the type described in Oversampling Delta-Sigma Data Converters , Candy and Temes Ed., IEEE Press 1992.
- a digital signal processor 32 for the audio path is provided to process the signals received from the A/D converter 30.
- the signals are split into low and high frequency bands or channels with adjustable corner frequencies in the processor 32.
- the gain, phase, and corner frequency of each channel are controlled by signals from a control processor 34.
- the signals from the two channels are then recombined.
- a digital-to-analog converter 36 is provided to convert the digital output signal stream from the audio signal processor 32 into a bit stream from which analog information, corresponding to the original acoustic input, can be recovered by low-pass filtering. This filtering occurs in the output transducer 28, the receiver for the aid 12.
- An output driver 36a drives the output transducer 28 (a magnetic receiver for example) in a switching type configuration. This arrangement provides high power conversion efficiency.
- the digital signal processor 34 for the control path 34 receives signals from the outputs of the two frequency channels of the audio signal processor 32 (best seen in Fig. 5) and produces control signals to provide real-time control of the gain of each channel. It also provides signals to control the corner frequency and phase of each channel.
- An instruction memory 34a coupled to the processor 34 provides instructions to the processor 34 to implement a control method. It will be understood that one of the advantages of the signal processor of Fig. 3 is that different control methods can be provided for different hearing deficiencies. Further, the method can be altered over time to take into account changes in a particular deficiency.
- Instructions can be loaded into the instruction memory 34 at the time of manufacture, or later if desired, via an interface processor 38.
- the memory 34a could be a non-volatile semiconductor memory.
- a parameter memory 34b provides control parameters to the control processor 34 to tailor the hearing aid characteristics to the hearing loss and needs of the hearing aid user.
- the parameter memory 34b preferably includes a volatile memory and a shadow non-volatile memory.
- Parameters may be loaded into the parameter memory 34b via the remote control unit 16, the wireless programmer 18 or the programming connector, such as connector 12a, and may be read from the parameter memory 34b via the wireless interface of the programming connector. Parameters can be transferred from the non-volatile portion of parameter memory 34b to the volatile portion when the hearing aid is turned on and may be transferred back and forth between these two memory types via commands from the remote control 16, the transmitter 18d or programming connector such as connector 12a.
- the parameter memory 34b also stores hearing aid identification data.
- a working memory 34c provides temporary storage for the working variables of the control processor 34.
- the interface processor 38 controls parallel or serial transmission or reception via input/output devices. These include the programming connector 12a or the remote control coil 22. When transmitting, serial data, for example, is provided, at connector 12a. Simultaneously the same signal is modulated and coupled to the coil 22'.
- the processor 38 also receives inputs from optional hearing aid mounted controls.
- the processor 38 provides control signals to the preamplifier 20a for selection of microphone and/or induction coil inputs.
- the electronic signal processor 24 can be partitioned into functions that are primarily analog and functions that are primarily digital in nature, as illustrated in Figure 3.
- the analog and digital functions can be integrated on separate chips to minimize the effects of digital noise on low level analog functions.
- the A/D converter 30 illustrated in block diagram form in Fig. 4 contains an analog summer 30-1 to add the analog input signal on the line 20b and an inverted feedback signal on a line 20c, producing an error signal on a line 30-2.
- First, second, and third analog integrators 30-3 to 30-5 in tandem, successively integrate the error signal.
- a feedback path 30-6 from the output of the third integrator 30-5 to the input of the second integrator 30-4 produces a zero in the transfer function at about 6000 Hz.
- a coefficient combiner 30-7 that provides a weighted sum of the analog outputs of the three integrators 30-3 to 30-5, provides a frequency weighted representation of the error signal.
- An analog clipping amplifier 30-8 amplifies the combined signal to a suitable level.
- a comparator 30-9 converts the amplified signal to a two-level (on/off) signal.
- a state detector 30-10 samples and latches the state of the comparator output at integer intervals of a clock (such as a 400 kHz rate).
- the output of the state detector 30-10 is the digital output of the A/D converter on a line 30-11.
- a pulse generator 30-12 produces a digital feedback signal consisting of a short pulse when the digital output is a logic zero and a long pulse when the digital output is a logic one.
- a one-bit D/A converter 30-13 inverts the digital feedback signal and converts it to an analog feedback on the line 20c with controlled signal levels.
- the audio signal processor 32 is illustrated in block diagram form in Figure 5. It contains a decimation stage 32-1 with a decimation filter and a decimeter that discards excess samples.
- the transfer function of the decimation filter is (1+Z -3 ) (1+Z -1 ) (1+Z -1 )/8 and every other sample is discarded, reducing a 400 kHz sample rate to 200 kHz.
- the audio signal processor 32 may be implemented without a decimation stage, but then subsequent digital filter stages must operate at twice the sample rate, reducing the possibilities of multiplexing filter elements.
- a band splitter and gain multiplier 32-2 multiplies the digital input by low-channel gain and phase values to provide an input to a low frequency channel filter 32-3, and multiplies the digital input by high-channel gain and phase values to provide the input to a high frequency channel filter 32-4.
- the high-channel filter 32-4 includes the following stages in series:
- This filter is implemented with adders and clocked registers and is multiplexed with a first order filter 32-6 in the low channel.
- a second-order high-pass digital filter 32-7 with a Q of .707 has a programmable corner frequency.
- This filter is implemented with multiplexed adders and clocked registers.
- a second-order low-pass digital filter 32-8 with a Q of 1.414 has a corner frequency of 5656 Hz.
- the purpose of this filter is to reduce the level of high frequency quantization noise. It is implemented with multiplexed adders and clocked registers.
- the low channel filter 32-3 includes the following stages in series:
- the first-order high-pass digital filter 32-6 with a corner frequency of 125 Hz. This filter is multiplexed with the first-order filter 32-5 in the high channel 32-4.
- This filter is implemented with multiplexed adders and clocked registers.
- a decimetor 32-12 decimates the outputs of both the high channel filter 32-4 and the low channel filter 32-3 by a factor of 16 to a sample rate of 12,500 samples/sec.
- Each decimation filter consists of a 16 sample sum and dump (sinc filter).
- the resulting high and low channel output signals are time multiplexed onto a single output bus 34-5.
- the D/A converter 36 is illustrated in Fig. 6. It includes an adder 36-1 that combines the digital input signal on the line 32-11 with an inverted two-valued digital feedback signal on a line 36-2 to produce an error signal on a line 36-3.
- An adder 36-7 is provided between the first and second accumulators 36-4 and 36-5 for injecting a feedback signal from the third accumulator 36-6 to introduce a transfer function zero at 5.6 kHz.
- An adder 36-8 provides a weighted sum of the digital outputs of the three accumulators 36-4 to 36-6, providing a frequency weighted representation of the error signal.
- a quantizer 36-9 provides a two-valued (one - bit) digital output from the multi-bit frequency weighted error signal on a line 36-9'. This is the first output of the D/A converter.
- An inverter 36-10 receives the first output and produces a second, inverted, output of the A/D converter on a line 36-11.
- the control processor 34 is illustrated in Fig. 7. It contains an instruction decoder 34-1 that receives instructions from the instruction memory 34a and status signals from various elements in the control processor. It provides signals to control the operation of the various processing elements and input and output selectors as well as to control read operations from the parameter memory 34b. It also controls read and write operations to the variable memory 34c.
- a program counter 34-2 controls the sequencing of instructions from the instruction memory 34a.
- a pair of general purpose counters 34-3 are available to be loaded, decremented, and tested by software.
- a pseudo-logarithmic converter 34-6 produces a piecewise linear approximation to the negative of log(base2) of the absolute value of the input. This operation produces a time multiplexed logarithmic representation of the signal magnitudes in the two channels 32-3 and 32-4.
- a pseudo-exponential converter 34-8 produces a piecewise linear approximation of exp(base 2) of the negative of the input. This converts the time multiplexed logarithmic representation of the gain control signals to linear domain gain multipliers for the two channels 32-3 and 32-4.
- a multiplier 34-10 is present in a first or in the "A" operand path 34-12 of the control processor 34. It multiplies the A input from “A" selector gates 34-14 by a 3 bit multiplicand or by the value 1 received from "M" selector gates 34-15.
- a barrel shifter 34-16 is located in the "A" operand path 34-12 after the multiplier 34-10.
- the shifter 34-16 left shifts the"A"operand 0 to 15 bit positions in response to a control input from shift selector gates 34-17.
- a conditional selector circuit 34-22 is coupled to the output of ALU 34-18.
- the selector which could be implemented with combinational gating, selects either the output of the ALU 34-18 or, in response to conditional select command from the "B" selector gating 34-19,selects either the "A" operand or the "B" operand depending on the Result ⁇ 0 output of the ALU.
- An accumulator 34-23 stores the output of the conditional selector 34-22 for one instruction cycle.
- a condition register 34-25 stores the condition test results of the ALU 34-18 for one instruction cycle.
- the "A" selector circuitry 34-14 for the "A" operand selects one of the following: a parameter obtained from the parameter memory 34b, the output of the accumulator 34-23, the magnitude signal from the high 32-4 or low 32-3 channel or an immediate operand from the instruction word from the instruction memory 34a.
- the "A" selector 34-14 supplies the first input to the multiplier 34-10.
- the "M" selector circuitry 34-15 selects either a parameter obtained from the parameter memory 34b, an immediate operand from the instruction word from the memory 34a or a multiplier of 1.
- the "S" selector circuitry 34-17 for the shift input of the barrel shifter 34-16 selects either a parameter obtained from the parameter memory 34b or an immediate operand obtained from the instruction from the memory 34a or a zero shift command.
- the "B" selector circuitry 34-19 for the "B" operand selects either a variable obtained from the variable memory 34c, the output of the accumulator 34-23, the volume control signal on a line 34-27 or an immediate operand obtained from the instruction word from the memory 34a.
- the interface processor 38 is illustrated in block diagram form in Fig. 8. It contains a pulse conditioner 38-1 that receives a signal stream from the remote control unit 16 via the remote signal detector coil 22'.
- the conditioner 38-1 provides envelope detection of this signal stream while also correcting for short spikes and drop outs.
- An input detector circuit 38-2 monitors incoming data from both the pulse conditioner 38-1 and the programming connector 12a. The detector waits for the presence of a conditioning pulse. When a conditioning pulse is received, the input detector 38-2 generates a control signal indicating that valid data is arriving. When the end of transmission is detected, the control signal is reset.
- a serial/parallel converter 38-3 shifts incoming serial data into a register and outputs 8-bit parallel data to a parallel data bus 38-5 at appropriate times.
- the serial/parallel converter 38-3 is also used to convert 8-bit parallel data to serial data when data is to be output to the programming connector 12a.
- a clock/bit-counter 38-6 controls the shifting of serial data in the serial/parallel converter 38-3 and times the transfer of parallel data to or from the parallel data bus 38-5.
- a parity check circuit 38-6' checks the parity of incoming data and generates an error signal if a parity error occurs.
- the parity check circuit 38-6' also provides the correct parity bit for data transmitted from the hearing aid 12, 14.
- a modulator 38-8 receives the data signals from coder circuit 38-7 and uses those signals to modulate a 50kHz carrier. This modulated signal is used to drive the tuned coil 22' providing wireless transmission.
- An ID control circuit 38-10 compares the first byte of an incoming transmission (the ID byte) to a stored ID byte identifier. If the ID bytes do not match, a signal is given to reset the serial interface and ignore the following transmission.
- a byte counter 38-14 identifies the incoming byte sequence and generates addresses for memory accesses.
- An interface control circuit 38-16 controls the operation of other elements in response to the commands that have been received.
- a microphone/telephone circuit 38-18 controls microphone or telephone coil selection based on commands received from the remote control or inputs from an optional hearing aid mounted M/T switch. It also controls a power-down function when a power-down command is received or if neither microphone nor telephone are selected.
- a volume control module 38-20 provides volume control setting information based on commands received from the remote control or from an optional hearing aid mounted volume control.
- a program select circuit 38-22 permits the selection of either pre-stored control program A or program B. This selection is in response to commands received from the connector, such as 12a or the coil 22'. Alternately, an optional switch mounted on the housing of the hearing aid 12, 14 can be used to select one of the pre-stored programs.
- the remote control unit 16 includes the following elements:
- the programming interface 18 provides for data transmission between a computer and a hearing aid or remote control unit.
- Fig. 10A is a block diagram of an interface 80 with programming plugs 18b, 18c.
- Fig. 10B is a block diagram of a wireless interface 82.
- a connector 80a mates with the parallel port of the personal computer 18a. That also allows a parallel data device such as a printer to be connected to the parallel port.
- Control logic 80b senses when the parallel port is to control the parallel data device and when it is to control the programming interface. The control logic also senses when data is being sent out by the computer 18a and when data is to be received and selects the proper signal path.
- the system for transmission or reception via programming cable of data to or from a hearing aid or remote control unit contains opto-isolators 84a, 84b and voltage translators 86a, 86b for converting between the voltage levels of the programming port and the control logic levels.
- One or more programming connectors 18b, 18c each having a bidirectional data line, a ground line, a supply voltage line connected to an isolated voltage supply or a battery.
- a circuit 88 for providing isolated supply voltage includes an oscillator 88a, a transformer 88b, a rectifier 88c, and a voltage regulator 88d.
- the system 82 for wireless transmission of commands and programs to the hearing aid contains the following elements:
- a system for wireless reception of data from the hearing aid contains the following elements:
Abstract
A hearing aid (12,14), having alterable
parameters, includes analog-to-digital input circuitry
(30) for forming a digital signal representative of an
incident acoustic wave. A digital signal processor
(32), coupled to said input circuitry (30), forms and
processes, at a first rate, first and second frequency
distinguishable data streams representative, at least
in part, of the digital signal. A control unit (34)
coupled to said processor (32) includes circuitry for
logarithmically processing at least one of the digital
data streams, at a reduced rate which is less than the
first rate. A parameter value storage memory (34b) is
coupled to the unit (34), and an interface (38) is
provided for accessing the memory (34b) and altering
parametric values stored therein.
Description
The invention pertains to electronic hearing
aids. More particularly, the invention pertains to
hearing aids which incorporate digital signal processors
for processing and amplifying incident acoustic waves as
well as equipment for programming such hearing aids.
Known forms of electronic hearing aids
incorporate circuitry for the purpose of processing and
amplifying an incident acoustic wave. The nature of the
processing and the degree of amplification that is
appropriate varies widely from one individual to
another.
There has been and continues to be an ongoing
need for electronic systems and hearing aids which in
addition to providing appropriate levels of gain and/or
other processing provide for ready modification of
processing characteristics so that standardized
circuitry can be used to meet the needs of a wide
variety of users. Additionally, the auditory
characteristics of any given individual vary over a
period of time and it would be particularly useful to be
able to alter processing characteristics or parameters
thereof after delivery and use of the hearing aid as
experience is gained with it. It would also be
desirable to rapidly and directly compare the effects of
such modifications.
It would be especially beneficial if such
processing characteristics and related parameters could
be modified in real-time while the hearing aid is
actually in use so as to maximize the beneficial effects
for the actual user. Further, it would be desirable to
be able to incorporate the benefits of digital signal
processing which can be carried out at relatively high
rates on the one hand with control methods or algorithms
which might allow processing at a lower rate so as to
achieve a more optimum result for the user.
Further, it would be desirable to be able to
carry out the complex calculations necessary for signal
processing without having to make extensive use of
multiplication and division operations which tend to
take longer than simpler operations such as addition or
subtraction. Finally, there continues to be a need to
carry out signal processing which will increase the
intelligibility of speech relative to noise which is
always present in the environment.
In accordance with an embodiment of a first aspect of the present
invention, an
input transducer which converts an incident audio wave
to an electrical signal is combined with an analog-to-digital
converter, a digital signal processor, a control
unit coupled to the digital signal processor and an
output transducer which carries out a low-pass filter
function simultaneously with generating an audible
output wave. The digital signal processor incorporates
a low-pass digital filter in combination with a high-pass
digital filter. The filters, in one aspect of the
invention, include one or more programmable corner
frequencies.
Digitized outputs from the filters are
combined in a summing stage. An output signal from the
summing stage is converted to an analog form in a
digital-to-analog converter and used to drive an output
transducer which also carries out a low-frequency
filtering operation.
In another aspect of the invention, a sigma-delta
analog-to-digital converter is coupled between
the input transducer and the digital signal processor.
A decimation circuit can be coupled between the output
of the converter and inputs to the signal paths of the
dual digital filters.
In yet another aspect of the invention, gain
control can be accomplished in the signal path by
multiplying a digital multi-bit gain control signal by a
one or two bit representation of the digitized input
signal, where there is no decimation circuitry.
Alternately, multiplication can be by a three to four
bit representation of the digital input signal in the
case of a circuit which carries out a decimation
function by a factor of 2.
In yet another aspect of the invention, the
digital filters can be operated at high oversampling
rates and can provide adjustable characteristic
frequencies determined by filter coefficients which are
binary based. The use of binary based filter
coefficients eliminates any need for multipliers.
Multiplication can be carried out by using shift
operations. These could be implemented using
multiplexer circuits for variable multiplications and
hard wired offsets for fixed multiplications.
In yet another aspect of the invention, the
output digital-to-analog converter can be implemented
without needing any additional filters beyond the low -
pass characteristic of the output transducer.
In yet another aspect of the invention, signal
amplitudes which have been digitized can be converted to
logarithmic form. In logarithmic form, additions and
subtractions replace multiplications and divisions.
Multiplication steps can be used to approximate
exponential functions.
In yet another aspect of the invention,
circuit simplicity is promoted by use of a piecewise
linear approximation to a logarithmic function. After
processing, the resulting signals are converted back to
a linear domain using a piecewise linear approximation
to an exponential function.
By translating various of the control signals
to a logarithmic representation, not only is circuit
complexity reduced, but the logarithmic domain readily
supports a wide dynamic range very efficiently. As a
result, dual input compression systems, dual output
compression systems and a noise reduction system can be
provided for each of the frequency bands and can be
independently adjustable.
In yet another aspect of the invention, the
hearing aid can include a programmable processor wherein
control instructions can be stored in nonvolatile
instruction memory when the unit is manufactured. This
allows units to be built with different sets of
instructions implementing different signal processing
algorithms.
In yet another aspect of the invention, one or
more interfaces can be provided to enable the control
unit to communicate with external circuitry. In one
aspect, the interface can be directly coupled to an
external programming apparatus for the purpose of
reading out the values of parameters stored within the
hearing aid and for adjusting parameters.
In yet another aspect of the invention, a
remote control unit can be provided. Such a unit could
transmit a modulated RF carrier which could be detected
by the interface of the hearing aid. Such an
arrangement would make it possible to remotely control
parameters of the aid so as to optimize performance
thereof in view of the individual characteristics of a
user and of the specific listening situation.
The remote control unit can be coupled with a
computer for the purpose of adjusting each of a number
of sets of parameters stored within the remote control
unit.
Further, in accordance with the yet another
aspect of the invention, a plurality of parameters are
field programmable for each of the channels of the
digital signal processor. Such parameters can be
established or modified based on user characteristics as
a result of being field programmable. As user
characteristics vary over time, the parameters may be
readily altered to take such variations into account.
A digital hearing aid in accordance with
another aspect of the invention incorporates a sigma-delta
A/D converter with either no decimation or with
decimation by a factor of 2. This reduces substantially
the amount of digital signal processing needed for
decimation filtering.
Further, using a sigma-delta A/D converter in
which pulse width modulation (return-to-zero coding) is
used in the digital feedback path eliminates the problem
of inaccuracy and noise caused by unequal rise and fall
times.
Gain control can be accomplished by
multiplying a digital multibit gain control signal by a
1 or 2 bit representation of the digital input signal
(in the case of no decimation) or by a 3 or 4 bit
representation of the digital input signal (in the case
of decimation by a factor of 2). This reduces
substantially the complexity of the multiplier.
Using infinite impulse response (IIR) digital
filters designed to operate at high oversampling rates
and providing adjustable characteristic frequencies
determined by filter coefficients that have values of 2-n,
where n is an integer eliminates the need for
multipliers, since the coefficients can be implemented
as digital shifts.
Using a sigma-delta D/A converter to produce
an output bit stream with no signal reconstruction
filter, relying on the low pass characteristic of the
output transducer to filter out high frequency
components and relying on the inductive impedance of the
output transducer to achieve high efficiency eliminates
the need for a reconstruction filter and provides a
highly efficient output drive to a magnetic transducer.
A digital hearing aid embodying yet
another aspect of the invention uses a digitally
rectified, filtered, and decimated version of the output
signal in each frequency band to represent the signal
amplitude in that band. Digital implementation of these
functions is accurate and efficient and requires no off-chip
components. Decimation to a low sampling rate
allows the control path to operate at a much reduced
computation rate.
Converting signal amplitude to a logarithmic
domain using a piecewise linear approximation to a
logarithmic function and then, after processing these
signals using a control algorithm, converting the
resulting control signals back to the linear domain
using a piecewise linear approximation to an exponential
function reduces hardware requirements. Multiplications
and divisions are replaced by additions and subtractions
and exponentials are replaced by rudimentary
multiplications, greatly reducing circuit complexity.
Also, the logarithmic domain expresses a wide dynamic
range very efficiently. This allows providing enough
capability to provide a dual input compression system, a
dual output compression system, and a noise reduction
system, with each of these independently adjustable for
each of two frequency bands.
A control processor that concurrently performs
the operations of selection of two input operands,
multiplication or shift, addition or subtraction or
conditional selection, and output storage allows more
processing per cycle than consecutive operation.
Implementing a control algorithm using
instructions programmed into a non-volatile instruction
memory at the time of manufacture of the hearing aid
permits rapid implementation of corrections or
improvements in the control algorithm.
A hearing aid with a digital serial interface
in accordance with the present invention can use pulse
width modulation (return-to-zero coding) for the
transmitted data. As a result, the transmitted signal
is self clocking so that a separate clock line is not
needed and timing is not critical. Also, since only a
single signal line is used, it is readily adaptable to
wireless communication.
A hearing aid that uses a serial interface can
provide some or all of the following functions:
Using a single interface for these functions
reduces cost and complexity.
A hearing aid with a serial interface that
includes an antenna switch and a carrier modulator so
that the same tuned coil can be used as both a receive
and transmit antenna. This permits wireless
transmission in both directions, eliminating the need
for a programming connector. A single tuned coil
antenna, saves cost and space. 50kHz pulse width
modulation transfers a binary bit stream.
A remote control for a hearing aid that
embodies the present invention can use pulse width
modulation of a 50kHz induction field (RF) carrier for
data transmission. The carrier frequency is well beyond
the audio band to minimize audible interference, but
still below allocated frequencies. The induction field
is not subject to body shadow effects and allows control
of both hearing aids in a binaural fitting from the same
remote control location. Pulse modulation allows highly
efficient output stage.
A remote control for a hearing aid that
embodies the present invention can use two transmitting
coils in space quadrature, driven with carriers in phase
quadrature. This minimizes nulls in the pickup pattern
of the transmitted signal.
In a further aspect of the invention, a remote
control for a hearing aid can use a conditioning pulse
and a transmitted identification number to signal a
valid transmission for the hearing aid being controlled.
This minimizes false actuation or actuation by another
user and permits independent control of both hearing
aids of a binaural pair.
A remote control that uses tuned coils driven
by a bridge type output in a switching mode provides
high transmitter efficiency.
In a further aspect of the invention, a remote
control having a programming connector enables a
computer to program multiple memories in the remote
control and that also enables a computer to program
memories in the hearing aid using wireless transmission
from the remote control to the hearing aid. Hence,
wireless programming of the hearing aid can be effected
using the modulator and transmitter already existing in
the remote control.
In a further aspect of the invention, a
hearing aid with a remote control that uses the same
induction coil for receiving the remote control signal
and for telephone induction pickup and induction loop
pick up has reduced space requirements and cost. This
remote control uses the same low frequency RF
transmission for both the phone and remote control
scheme. Both uses the same coil in and out.
A hearing aid for use with this remote
control uses AGC acting on the tuned receiver coil to
control the sensitivity for the remote control signal
while not affecting sensitivity for audio frequency
induction signals. This reduces audible interference
from the remote control.
In a further aspect of the invention, a
computer interface permits programming hearing aids or
remote controls that uses a computer parallel port to
supply power for the interface and to provide
bidirectional communication. This eliminates the size,
cost, and inconvenience of a separate power supply. The
computer software is able to control the signal
switching pattern. Such a computer interface makes it
possible to program hearing aids or remote controls by
use of a transformer to transmit power to the interface
and optocouplers to transmit signals to and from the
interface. This provides electrical isolation needed to
meet safety requirements.
A hearing aid embodying the present
invention can incorporate a signal-processing algorithm
in which numerous parameters are field programmable over
selected ranges in each of two channels. These include:
Full-on Gain: 48 dB range in 3 dB increments.
Corner Frequency: 500, 707, 1000, 1414, 2000, 2828, or 4000 Hz. Phase: In phase or out of phase.
Primary Output AGC System
Full-on Gain: 48 dB range in 3 dB increments.
Corner Frequency: 500, 707, 1000, 1414, 2000, 2828, or 4000 Hz. Phase: In phase or out of phase.
Primary Output AGC System
- Limiting Level: 48 dB range in 3 dB increments.
- Release Time: 2 to 8192 msec in powers of 2.
- Threshold Level: 48 dB range in 3 dB increments.
- Compression Ratio: 1.14, 1.33, 1.6, 2.67, 4, or 8.
- Attack Time: 2 to 8192 msec in powers of 2.
- Release Time: 2 to 8192 msec in powers of 2.
- Threshold Level: 48 dB range in 3 dB increments.
- Compression Ratio: 1.14, 1.33, 1.6, 2.67, 4, or 8.
- Attack Time: 2 to 8192 msec in powers of 2.
- Release Time: 2 to 8192 msec in powers of 2.
- Threshold Level: 48 dB range in 3 dB increments.
- Attack Time: 2 to 8192 msec in powers of 2.
The following parameters may be programmed at
the time of hearing aid manufacture over various ranges
in each of two channels.
Secondary Output AGC System
Noise Reduction System
A fitting system can be provided that uses a
fitting algorithm to select hearing aid parameters based
on the factors of abnormal growth of loudness, widening
of critical bands, abnormal upward spread of masking,
and binaural vs. monaural fitting.
Reference will now be made, by way of example, to the
accompanying drawings, in which:-
While this invention is susceptible of
embodiment in many different forms, there is shown in
the drawings and will be described herein in detail,
specific embodiments thereof with the understanding that
the present disclosure is to be considered as an
exemplification of the principles of the invention and
is not intended to limit the invention to the specific
embodiments illustrated.
A digital hearing aid system 10 of Fig. 1
contains digital hearing aids 12, 14 (binaural fitting)
or a single digital hearing aid 12 or 14 (monaural
fitting) worn by the user. The hearing aids 12, 14 are
optionally equipped with programming sockets 12a, 14a to
allow the hearing aid characteristics to be programmed
for the individual user.
A remote control unit 16 is carried by the user
to control the operation of the hearing aid(s) 12, 14.
The unit 16 is capable of transmitting, via radiant
electromagnetic energy R, user-selected commands and
parameter sets to the hearing aid(s) 12, 14 to adjust
the hearing aids characteristics for various listening
environments. The remote control unit 16 is equipped
with a programming socket 16a to allow entering and storing
of a number of user-selectable programs or
parameter values.
A programming interface 18 is coupled to a
personal computer 18a. Programming cords and plugs 18b, 18c
transmit the electrical signals needed to program the
hearing aid(s) 12, 14 and remote control unit 16.
Alternately, the hearing aids 12, 14 are
equipped with a wireless transmitter 18d and receiver
18e. The hearing aids 12, 14 can thus be remotely
programmed or controlled. In addition, pickup 18e' can
detect previously stored programs or data being read
back to receiver 18e.
A fitting program 18f can be run on the
personal computer 18a to accept audiological data for
the user, to determine the appropriate characteristics
of the hearing aid(s) 12, 14 for that user, and to
provide the appropriate data to the programming
interface 18. The fitting program 18f can also provide
other functions, such as storage and retrieval of user -
specific data.
The hearing aid system 10 may be provided in
various forms. For example, the hearing aid(s) 12, 14
may be behind-the-ear (BTE), in-the-ear (ITE), or in -
the-canal type. Also the system 10 may be configured
without the remote control unit 16, using a limited set
of hearing aid mounted controls instead. The system 10
may even be configured with no user operated control
other than an on/off switch.
Fig. 2 illustrates a block diagram for a
hearing aid such as the aid(s) 12, 14.
The digital hearing aid(s) 12, 14 of Fig. 2
each contain a microphone 20 to receive acoustic signals
in the audio frequency band. An inductive pickup coil
22 serves multiple a dual purposes.
The coil 22 receives magnetic field signals in
the audio frequency band from a telephone receiver or a
transmitting induction loop. It can also receive remote
control signals encoded on a transmitted or radiated
electromagnetic carrier whose frequency is above the
audio band. It can also be used to receive programming
signals from transmitter 18d or to transmit programs or
information to receiver 18e. For a hearing aid without
an induction pickup option and without remote control
and wireless options, the induction coil 22 is not
needed.
The connector 12a can optionally be provided
for bidirectional transfer of encoded programming
signals. Transfer can be in serial or parallel.
An electronic signal processor 24 receives the
above signals together with control signals from
optional hearing aid mounted controls 26 and provides an
electrical output signal at an output port 24a. A
receiver 28 converts this electrical output signal to an
acoustic output signal.
A battery provides power for the electronic
signal processor 24.
The electronic signal processor 24 is
illustrated in block diagram form in Fig. 3. The
following table further explains the nature of the
signals S1 to S21 shown in Figure 3.
- S1
- Analog - audio freq.
- S2
- 1 bit 400 KHz
- S3
- 13 bits 400 KHz
- S4
- 2 bits 400 KHz
- S5
- 2 line output, audio with 400 KHz carrier
- S6
- analog - audio freq.
- S7
- control signals
- S8
- analog
- S9
- analog
- S10
- modulated 50 KHz carrier
- S11
- 1 bit digital serial data
- S12
- control lines
- S13
- address; data; control
- S14
- address; data; control
- S15
-
data 24 bits - S16
- address bits
- S17
- 8 bit data
- S18
- address bits
- S19
- 9 bits parallel two interleved 12.5 Kbit signals
- S20
- 10 bits control signals
- S21
- 9 bits parallel two interleaved 12.5 Kbit rate signals
The processor 24 contains an induction coil
preamplifier 22a to amplify the audio frequency signals
and the remote control signals detected by the induction
coil 22. Automatic gain control (AGC), is included to
control the output level of the remote control signal.
A remote control signal detector 22b is
coupled to the preamplifier 22a to recover the
modulating signal from the carrier signal detected by
coil 22.
A preamplifier 20a is provided to amplify the
signal from the microphone 20 and/or the output signal
from the induction coil preamplifier 22a. AGC limiting
is included to prevent overloading by high input signal
levels.
An analog-to-digital converter 30 is provided
to convert the analog output of the preamplifier 20a to
a digital form. The A/D converter 30 is based on sigma-delta
modulation of the type described in Oversampling
Delta-Sigma Data Converters, Candy and Temes Ed., IEEE
Press 1992.
A digital signal processor 32 for the audio
path is provided to process the signals received from
the A/D converter 30. The signals are split into low
and high frequency bands or channels with adjustable
corner frequencies in the processor 32. The gain,
phase, and corner frequency of each channel are
controlled by signals from a control processor 34. The
signals from the two channels are then recombined.
A digital-to-analog converter 36 is provided
to convert the digital output signal stream from the
audio signal processor 32 into a bit stream from which
analog information, corresponding to the original
acoustic input, can be recovered by low-pass filtering.
This filtering occurs in the output transducer 28, the
receiver for the aid 12.
An output driver 36a drives the output
transducer 28 (a magnetic receiver for example) in a
switching type configuration. This arrangement provides
high power conversion efficiency.
The digital signal processor 34 for the
control path 34 receives signals from the outputs of the
two frequency channels of the audio signal processor 32
(best seen in Fig. 5) and produces control signals to
provide real-time control of the gain of each channel. It
also provides signals to control the corner frequency
and phase of each channel.
An instruction memory 34a coupled to the
processor 34 provides instructions to the processor 34
to implement a control method. It will be understood
that one of the advantages of the signal processor of
Fig. 3 is that different control methods can be provided
for different hearing deficiencies. Further, the method
can be altered over time to take into account changes in
a particular deficiency.
Instructions can be loaded into the
instruction memory 34 at the time of manufacture, or
later if desired, via an interface processor 38. The
memory 34a could be a non-volatile semiconductor memory.
A parameter memory 34b provides control
parameters to the control processor 34 to tailor the
hearing aid characteristics to the hearing loss and
needs of the hearing aid user. The parameter memory 34b
preferably includes a volatile memory and a shadow non-volatile
memory.
Parameters may be loaded into the parameter
memory 34b via the remote control unit 16, the wireless
programmer 18 or the programming connector, such as
connector 12a, and may be read from the parameter memory
34b via the wireless interface of the programming
connector. Parameters can be transferred from the non-volatile
portion of parameter memory 34b to the volatile
portion when the hearing aid is turned on and may be
transferred back and forth between these two memory
types via commands from the remote control 16, the
transmitter 18d or programming connector such as
connector 12a. The parameter memory 34b also stores
hearing aid identification data.
A working memory 34c provides temporary
storage for the working variables of the control
processor 34.
The interface processor 38 controls parallel
or serial transmission or reception via input/output
devices. These include the programming connector 12a or
the remote control coil 22. When transmitting, serial
data, for example, is provided, at connector 12a.
Simultaneously the same signal is modulated and coupled
to the coil 22'.
The processor 38 also receives inputs from
optional hearing aid mounted controls. The processor 38
provides control signals to the preamplifier 20a for
selection of microphone and/or induction coil inputs.
In addition various support functions are
provided, such as voltage regulation, clock generation,
and power-down functions. These functions are all a
type well known to those of skill in the art and as a
result are not addressed further.
The electronic signal processor 24 can be
partitioned into functions that are primarily analog and
functions that are primarily digital in nature, as
illustrated in Figure 3. The analog and digital
functions can be integrated on separate chips to
minimize the effects of digital noise on low level
analog functions.
The A/D converter 30 illustrated in block
diagram form in Fig. 4 contains an analog summer 30-1 to
add the analog input signal on the line 20b and an
inverted feedback signal on a line 20c, producing an
error signal on a line 30-2. First, second, and third
analog integrators 30-3 to 30-5, in tandem, successively
integrate the error signal. A feedback path 30-6 from
the output of the third integrator 30-5 to the input of
the second integrator 30-4 produces a zero in the
transfer function at about 6000 Hz.
A coefficient combiner 30-7 that provides a
weighted sum of the analog outputs of the three
integrators 30-3 to 30-5, provides a frequency weighted
representation of the error signal. An analog clipping
amplifier 30-8 amplifies the combined signal to a
suitable level.
A comparator 30-9 converts the amplified
signal to a two-level (on/off) signal. A state detector
30-10 samples and latches the state of the comparator
output at integer intervals of a clock (such as a 400
kHz rate). The output of the state detector 30-10 is
the digital output of the A/D converter on a line 30-11.
A pulse generator 30-12, produces a digital
feedback signal consisting of a short pulse when the
digital output is a logic zero and a long pulse when the
digital output is a logic one. A one-bit D/A converter
30-13 inverts the digital feedback signal and converts
it to an analog feedback on the line 20c with controlled
signal levels.
The audio signal processor 32 is illustrated
in block diagram form in Figure 5. It contains a
decimation stage 32-1 with a decimation filter and a
decimeter that discards excess samples. For decimation
by 2, the transfer function of the decimation filter is
(1+Z-3 ) (1+Z-1 ) (1+Z-1 )/8
and every other sample is discarded, reducing a 400 kHz
sample rate to 200 kHz.
The audio signal processor 32 may be
implemented without a decimation stage, but then
subsequent digital filter stages must operate at twice
the sample rate, reducing the possibilities of
multiplexing filter elements.
A band splitter and gain multiplier 32-2
multiplies the digital input by low-channel gain and
phase values to provide an input to a low frequency
channel filter 32-3, and multiplies the digital input by
high-channel gain and phase values to provide the input
to a high frequency channel filter 32-4.
The high-channel filter 32-4 includes the
following stages in series:
A first-order low-pass digital filter 32-5
with a corner frequency of 4000 Hz. This filter is
implemented with adders and clocked registers and is
multiplexed with a first order filter 32-6 in the low
channel.
A second-order high-pass digital filter 32-7
with a Q of .707 has a programmable corner frequency.
This filter is implemented with multiplexed adders and
clocked registers.
A second-order low-pass digital filter 32-8
with a Q of 1.414 has a corner frequency of 5656 Hz.
The purpose of this filter is to reduce the level of
high frequency quantization noise. It is implemented
with multiplexed adders and clocked registers.
The low channel filter 32-3 includes the
following stages in series:
The first-order high-pass digital filter 32-6
with a corner frequency of 125 Hz. This filter is
multiplexed with the first-order filter 32-5 in the high
channel 32-4.
A second-order low-pass digital filter 32-9
with a Q of .707 and a programmable corner frequency.
This filter is implemented with multiplexed adders and
clocked registers.
A sum and limit stage 32-10 limits the signal
range of the digital inputs from the high and low
channels, adds them, and then again limits the range of
the summed signal on a line 32 -11. The result is the
output signal from the audio signal processor 32.
A decimetor 32-12 decimates the outputs of
both the high channel filter 32-4 and the low channel
filter 32-3 by a factor of 16 to a sample rate of 12,500
samples/sec. Each decimation filter consists of a 16
sample sum and dump (sinc filter). The resulting high
and low channel output signals are time multiplexed onto
a single output bus 34-5.
The D/A converter 36 is illustrated in Fig. 6.
It includes an adder 36-1 that combines the digital
input signal on the line 32-11 with an inverted two-valued
digital feedback signal on a line 36-2 to produce
an error signal on a line 36-3.
First, second, and third accumulators or
registers 36-4 to 36-6 in series, successively
accumulate the error signal.
An adder 36-7 is provided between the first
and second accumulators 36-4 and 36-5 for injecting a
feedback signal from the third accumulator 36-6 to
introduce a transfer function zero at 5.6 kHz.
An adder 36-8 provides a weighted sum of the
digital outputs of the three accumulators 36-4 to 36-6,
providing a frequency weighted representation of the
error signal.
A quantizer 36-9 provides a two-valued (one -
bit) digital output from the multi-bit frequency
weighted error signal on a line 36-9'. This is the
first output of the D/A converter.
An inverter 36-10 receives the first output
and produces a second, inverted, output of the A/D
converter on a line 36-11.
The control processor 34 is illustrated in
Fig. 7. It contains an instruction decoder 34-1 that
receives instructions from the instruction memory 34a
and status signals from various elements in the control
processor. It provides signals to control the operation
of the various processing elements and input and output
selectors as well as to control read operations from the
parameter memory 34b. It also controls read and write
operations to the variable memory 34c.
A program counter 34-2 controls the sequencing
of instructions from the instruction memory 34a. A pair
of general purpose counters 34-3 are available to be
loaded, decremented, and tested by software.
A pseudo-logarithmic converter 34-6 produces a
piecewise linear approximation to the negative of
log(base2) of the absolute value of the input. This
operation produces a time multiplexed logarithmic
representation of the signal magnitudes in the two
channels 32-3 and 32-4.
A pseudo-exponential converter 34-8 produces a
piecewise linear approximation of exp(base 2) of the
negative of the input. This converts the time
multiplexed logarithmic representation of the gain
control signals to linear domain gain multipliers for
the two channels 32-3 and 32-4.
A multiplier 34-10 is present in a first or in
the "A" operand path 34-12 of the control processor 34.
It multiplies the A input from "A" selector gates 34-14
by a 3 bit multiplicand or by the value 1 received from
"M" selector gates 34-15.
A barrel shifter 34-16 is located in the "A"
operand path 34-12 after the multiplier 34-10. The
shifter 34-16 left shifts the"A"operand 0 to 15 bit
positions in response to a control input from shift
selector gates 34-17.
An arithmetic and logic unit (ALU) 34-18
receives an "A." operand from the barrel shifter 34-16
and a "B" operand from a "B" input selector circuit 34-19.
It performs the operations of addition (A+B),
subtraction (A-B), and tests for the conditions
Result=zero and Result<zero.
A conditional selector circuit 34-22 is
coupled to the output of ALU 34-18. The selector, which
could be implemented with combinational gating, selects
either the output of the ALU 34-18 or, in response to
conditional select command from the "B" selector gating
34-19,selects either the "A" operand or the "B" operand
depending on the Result <0 output of the ALU.
An accumulator 34-23 stores the output of the
conditional selector 34-22 for one instruction cycle. A
condition register 34-25 stores the condition test
results of the ALU 34-18 for one instruction cycle.
The "A" selector circuitry 34-14 for the "A"
operand selects one of the following: a parameter
obtained from the parameter memory 34b, the output of
the accumulator 34-23, the magnitude signal from the
high 32-4 or low 32-3 channel or an immediate operand
from the instruction word from the instruction memory
34a. The "A" selector 34-14 supplies the first input to
the multiplier 34-10.
The "M" selector circuitry 34-15, the second
input to the multiplier 34-10, selects either a parameter
obtained from the parameter memory 34b, an immediate operand
from the instruction word from the memory 34a or a
multiplier of 1.
The "S" selector circuitry 34-17 for the shift
input of the barrel shifter 34-16 selects either a
parameter obtained from the parameter memory 34b or an
immediate operand obtained from the instruction from the
memory 34a or a zero shift command.
The "B" selector circuitry 34-19 for the "B"
operand selects either a variable obtained from the
variable memory 34c, the output of the accumulator 34-23,
the volume control signal on a line 34-27 or an
immediate operand obtained from the instruction word
from the memory 34a.
A frequency register 34-29 latches the channel
frequency and phase parameters when the first two
parameter addresses are accessed.
The interface processor 38 is illustrated in
block diagram form in Fig. 8. It contains a pulse
conditioner 38-1 that receives a signal stream from the
remote control unit 16 via the remote signal detector
coil 22'. The conditioner 38-1 provides envelope
detection of this signal stream while also correcting
for short spikes and drop outs.
An input detector circuit 38-2 monitors
incoming data from both the pulse conditioner 38-1 and
the programming connector 12a. The detector waits for
the presence of a conditioning pulse. When a
conditioning pulse is received, the input detector 38-2
generates a control signal indicating that valid data is
arriving. When the end of transmission is detected, the
control signal is reset.
A serial/parallel converter 38-3 shifts
incoming serial data into a register and outputs 8-bit
parallel data to a parallel data bus 38-5 at appropriate
times. The serial/parallel converter 38-3 is also used
to convert 8-bit parallel data to serial data when data
is to be output to the programming connector 12a.
A clock/bit-counter 38-6 controls the shifting
of serial data in the serial/parallel converter 38-3 and
times the transfer of parallel data to or from the
parallel data bus 38-5.
A parity check circuit 38-6' checks the parity
of incoming data and generates an error signal if a
parity error occurs. The parity check circuit 38-6'
also provides the correct parity bit for data
transmitted from the hearing aid 12, 14.
A coder circuit 38-7 provides a serial output
data stream to programming connector 12a and to coil
22'. The coder 38-7 produces a short pulse for each
zero bit to be transmitted out to the programming
connector 12a and a long pulse for each one bit.
A modulator 38-8 receives the data signals
from coder circuit 38-7 and uses those signals to
modulate a 50kHz carrier. This modulated signal is used
to drive the tuned coil 22' providing wireless
transmission.
An antenna switch 38-9 switches coil 22'
between receive and transmit modes. In the receive mode
it is coupled to the coil preamplifier 22a. In the
transmit mode it is disconnected from that preamplifier
and coupled to the modulator 38-8.
An ID control circuit 38-10 compares the first
byte of an incoming transmission (the ID byte) to a
stored ID byte identifier. If the ID bytes do not
match, a signal is given to reset the serial interface
and ignore the following transmission.
A command latch 38-12 latches the second byte
of an incoming transmission (the command byte). The
command byte consists of the following command bits:
- PWDN
- command to power-down the hearing aid to conserve power when not in active use.
- VUP
- command to increase the volume setting of the hearing aid.
- VDN
- command to decrease the volume setting of the hearing aid.
- RD
- command to read out, by subsequent bytes sent out via the serial port, the parameters representing the current settings of the hearing aid.
- WRT
- command to write to the hearing aid, by subsequent bytes sent in via the serial port, the parameters representing a new setting of the hearing aid.
- RCL
- command to recall parameters from the non-volatile portion of the parameter memory to the working portion, making these parameters the current setting of the hearing aid.
- STO
- command to store the parameters in the working portion of the parameter memory to the non-volatile portion.
- PRG
- command to select stored control program A or control program B.
A byte counter 38-14 identifies the incoming
byte sequence and generates addresses for memory
accesses. An interface control circuit 38-16 controls
the operation of other elements in response to the
commands that have been received.
A microphone/telephone circuit 38-18 controls
microphone or telephone coil selection based on commands
received from the remote control or inputs from an
optional hearing aid mounted M/T switch. It also
controls a power-down function when a power-down command
is received or if neither microphone nor telephone are
selected.
A volume control module 38-20 provides volume
control setting information based on commands received
from the remote control or from an optional hearing aid
mounted volume control.
A program select circuit 38-22 permits the
selection of either pre-stored control program A or
program B. This selection is in response to commands
received from the connector, such as 12a or the coil
22'. Alternately, an optional switch mounted on the
housing of the hearing aid 12, 14 can be used to select
one of the pre-stored programs.
With respect to Fig. 9, the remote control
unit 16 includes the following elements:
The programming interface 18 provides for data
transmission between a computer and a hearing aid or
remote control unit. Fig. 10A is a block diagram of an
interface 80 with programming plugs 18b, 18c. Fig. 10B
is a block diagram of a wireless interface 82.
In the interface 80, a connector 80a mates
with the parallel port of the personal computer 18a.
That also allows a parallel data device such as a
printer to be connected to the parallel port. Control
logic 80b senses when the parallel port is to control
the parallel data device and when it is to control the
programming interface. The control logic also senses
when data is being sent out by the computer 18a and when
data is to be received and selects the proper signal
path.
The system for transmission or reception via
programming cable of data to or from a hearing aid or
remote control unit contains opto- isolators 84a, 84b and
voltage translators 86a, 86b for converting between the
voltage levels of the programming port and the control
logic levels.
One or more programming connectors 18b, 18c
each having a bidirectional data line, a ground line, a
supply voltage line connected to an isolated voltage
supply or a battery.
Alternately, when only a small amount of power
is needed, the power supply can be derived by drawing
power from the data lines of the parallel port. A
circuit 88 for providing isolated supply voltage
includes an oscillator 88a, a transformer 88b, a
rectifier 88c, and a voltage regulator 88d.
The system 82 for wireless transmission of
commands and programs to the hearing aid, contains the
following elements:
A system for wireless reception of data from
the hearing aid contains the following elements:
From the foregoing, it will be observed that
numerous variations and modifications may be effected
without departing from the spirit and scope of the
invention. It is to be understood that no limitation
with respect to the specific apparatus illustrated
herein is intended or should be inferred. It is, of
course, intended to cover by the appended claims all
such modifications as fall within the scope of the
claims.
Claims (10)
- A hearing aid, having alterable parameters, comprising:analog-to-digital input circuitry (30) for forming a digital signal representative of an incident acoustic wave;a digital signal processor (32), coupled to said input circuitry (30), wherein said processor forms and processes first and second, frequency distinguishable, data streams representative, at least in part, of said digital signal, at a first rate;a control unit (34), coupled to said processor (32), wherein said unit (34) includes circuitry for logarithmically processing at least one of said digital data streams, at a reduced rate, less than said first rate;parameter value storage memory (34b) coupled to said unit; andan interface (38) for accessing said memory (34b) and altering parametric values stored therein.
- An aid as claimed in claim 1, wherein said control unit includes decimation circuitry.
- An aid as claimed in claim 1, wherein said processor (32) includes first and second digital filters (32-3, 32-4).
- An aid as claimed in claim 3, wherein said control unit interacts with and converts said data streams to logarithmic representations of said digital signal.
- An aid as claimed in claim 3, wherein said processor includes combining circuitry for forming a single, output, digitized, data stream representative of said digital signal.
- An aid as claimed in claim 1, wherein said interface (38) includes a receiver of remotely generated wireless signals.
- An aid as claimed in claim 6, wherein said interface (38) further includes a transmitter of wireless signals.
- An aid as claimed in claim 1, wherein said interface (38) is accessible by transmitted radiant energy.
- An aid as claimed in claim 1, wherein said control unit includes an instruction storage memory.
- An aid as claimed in claim 1, wherein said processor includes first and second, parallel, digital filters wherein each said filter has a plurality of parameters associated therewith and wherein at least some of said parameters are remotely alterable via said interface.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US69102896A | 1996-08-07 | 1996-08-07 | |
US691028 | 1996-08-07 |
Publications (2)
Publication Number | Publication Date |
---|---|
EP0823829A2 true EP0823829A2 (en) | 1998-02-11 |
EP0823829A3 EP0823829A3 (en) | 2000-01-26 |
Family
ID=24774888
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP97305981A Withdrawn EP0823829A3 (en) | 1996-08-07 | 1997-08-06 | Digital hearing aid system |
Country Status (3)
Country | Link |
---|---|
EP (1) | EP0823829A3 (en) |
JP (1) | JPH10126895A (en) |
CA (1) | CA2212131A1 (en) |
Cited By (31)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2000016589A1 (en) * | 1998-09-17 | 2000-03-23 | Sonic Innovations, Inc. | Two line variable word length serial interface |
WO2001035695A2 (en) * | 1999-11-12 | 2001-05-17 | Siemens Hearing Instruments, Inc. | Patient isolating programming interface for programming hearing aids |
EP1118249A1 (en) * | 1998-09-14 | 2001-07-25 | Micro Ear Technology, Inc. | System for programming hearing aids |
US6313773B1 (en) | 2000-01-26 | 2001-11-06 | Sonic Innovations, Inc. | Multiplierless interpolator for a delta-sigma digital to analog converter |
EP1196006A2 (en) * | 2000-10-03 | 2002-04-10 | FreeSystems Pte Ltd | On-demand audio entertainment device that allows wireless download content |
US6408318B1 (en) | 1999-04-05 | 2002-06-18 | Xiaoling Fang | Multiple stage decimation filter |
EP1250026A1 (en) * | 2001-04-11 | 2002-10-16 | Phonic Ear, Inc. | Short range data transfer for communication devices |
US6480610B1 (en) | 1999-09-21 | 2002-11-12 | Sonic Innovations, Inc. | Subband acoustic feedback cancellation in hearing aids |
US6574342B1 (en) | 1998-03-17 | 2003-06-03 | Sonic Innovations, Inc. | Hearing aid fitting system |
US6757395B1 (en) | 2000-01-12 | 2004-06-29 | Sonic Innovations, Inc. | Noise reduction apparatus and method |
EP1538873A2 (en) * | 2003-12-01 | 2005-06-08 | Siemens Audiologische Technik GmbH | Hearing aid with wireless transmission system and corresponding transmission method |
WO2005107319A1 (en) * | 2004-04-29 | 2005-11-10 | Jetta Company Limited | Digital noise filter system and related apparatus and method |
DE102005016017A1 (en) * | 2005-04-07 | 2006-10-19 | Siemens Audiologische Technik Gmbh | Hearing aid device, has telephone coil utilized as antenna for high frequency signals above one mega Hertz, where evaluator is provided for evaluating high frequency signals of telephone coil |
WO2008074323A3 (en) * | 2006-12-21 | 2008-08-07 | Gn Resound As | Hearing instrument with user interface |
DE102007018121A1 (en) * | 2007-04-16 | 2008-10-30 | Siemens Medical Instruments Pte. Ltd. | Hearing device with low-noise handset control and corresponding method |
EP1410684B1 (en) * | 2001-06-28 | 2009-01-28 | Oticon A/S | Hearing aid fitting |
CN101611637A (en) * | 2006-12-21 | 2009-12-23 | Gn瑞声达A/S | Hearing device with user interface |
EP2190217A1 (en) * | 2008-11-24 | 2010-05-26 | Oticon A/S | Method to reduce feedback in hearing aids |
US7929723B2 (en) | 1997-01-13 | 2011-04-19 | Micro Ear Technology, Inc. | Portable system for programming hearing aids |
US8107657B2 (en) | 2002-07-12 | 2012-01-31 | Widex A/S | Hearing aid and a method for enhancing speech intelligibility |
US8224004B2 (en) | 2006-09-08 | 2012-07-17 | Phonak Ag | Programmable remote control |
US8300862B2 (en) | 2006-09-18 | 2012-10-30 | Starkey Kaboratories, Inc | Wireless interface for programming hearing assistance devices |
WO2013001508A2 (en) * | 2011-06-29 | 2013-01-03 | Cochlear Limited | Systems, methods, and article of manufacture for configuring a hearing prosthesis |
US8520881B2 (en) | 2007-04-16 | 2013-08-27 | Siemens Medical Instruments Pte. Ltd. | Hearing apparatus with low-interference receiver control and corresponding method |
US8532318B2 (en) | 2009-10-13 | 2013-09-10 | Panasonic Corporation | Hearing aid device |
CN103491491A (en) * | 2013-09-22 | 2014-01-01 | 江苏贝泰福医疗科技有限公司 | Full-digital hearing aid and non-traditional hearing aid fitting method |
US8842863B2 (en) | 2009-04-06 | 2014-09-23 | Widex A/S | Two part hearing aid with databus connection |
EP1694095A3 (en) * | 2005-02-15 | 2016-04-27 | Sivantos GmbH | Hearing aid with an output amplifier comprising a sigma-delta modulator |
US9344817B2 (en) | 2000-01-20 | 2016-05-17 | Starkey Laboratories, Inc. | Hearing aid systems |
US10225667B2 (en) | 2015-03-10 | 2019-03-05 | Sivantos Pte. Ltd. | Method and hearing aid for frequency-dependent reduction of noise in an input signal |
US11602632B2 (en) | 2014-09-30 | 2023-03-14 | Cochlear Limited | User interfaces of a hearing device |
Families Citing this family (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
AU2571900A (en) | 1999-02-16 | 2000-09-04 | Yugen Kaisha Gm&M | Speech converting device and method |
ATE404033T1 (en) * | 2005-01-17 | 2008-08-15 | Widex As | DEVICE AND METHOD FOR OPERATING A HEARING AID |
JP5292098B2 (en) * | 2005-10-18 | 2013-09-18 | ヴェーデクス・アクティーセルスカプ | Hearing aid programming device and hearing aid |
JP4750153B2 (en) * | 2008-05-28 | 2011-08-17 | 独立行政法人科学技術振興機構 | Acoustic device and acoustic adjustment method |
US9439008B2 (en) | 2013-07-16 | 2016-09-06 | iHear Medical, Inc. | Online hearing aid fitting system and methods for non-expert user |
US9031247B2 (en) * | 2013-07-16 | 2015-05-12 | iHear Medical, Inc. | Hearing aid fitting systems and methods using sound segments representing relevant soundscape |
EP3152919B1 (en) | 2014-06-03 | 2020-02-19 | Dolby Laboratories Licensing Corporation | Passive and active virtual height filter systems for upward firing drivers |
CN112788487B (en) | 2014-06-03 | 2022-05-27 | 杜比实验室特许公司 | Crossover circuit, loudspeaker and audio scene generation method and equipment |
US20160066822A1 (en) | 2014-09-08 | 2016-03-10 | iHear Medical, Inc. | Hearing test system for non-expert user with built-in calibration and method |
CN104754485B (en) * | 2015-02-06 | 2018-04-06 | 哈尔滨工业大学深圳研究生院 | A kind of digital deaf-aid echo canceling method based on NLMS algorithm improvements |
EP3384686A4 (en) | 2015-12-04 | 2019-08-21 | Ihear Medical Inc. | Self-fitting of a hearing device |
WO2019136382A1 (en) * | 2018-01-05 | 2019-07-11 | Laslo Olah | Hearing aid and method for use of same |
Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4852175A (en) * | 1988-02-03 | 1989-07-25 | Siemens Hearing Instr Inc | Hearing aid signal-processing system |
EP0339819A2 (en) * | 1988-04-11 | 1989-11-02 | Central Institute For The Deaf | Electronic filter |
US5029217A (en) * | 1986-01-21 | 1991-07-02 | Harold Antin | Digital hearing enhancement apparatus |
EP0448764A1 (en) * | 1990-03-30 | 1991-10-02 | Siemens Audiologische Technik GmbH | Programmable electrical hearing aid |
WO1997014266A2 (en) * | 1995-10-10 | 1997-04-17 | Audiologic, Inc. | Digital signal processing hearing aid with processing strategy selection |
-
1997
- 1997-07-31 CA CA002212131A patent/CA2212131A1/en not_active Abandoned
- 1997-08-06 EP EP97305981A patent/EP0823829A3/en not_active Withdrawn
- 1997-08-07 JP JP9245877A patent/JPH10126895A/en active Pending
Patent Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5029217A (en) * | 1986-01-21 | 1991-07-02 | Harold Antin | Digital hearing enhancement apparatus |
US4852175A (en) * | 1988-02-03 | 1989-07-25 | Siemens Hearing Instr Inc | Hearing aid signal-processing system |
EP0339819A2 (en) * | 1988-04-11 | 1989-11-02 | Central Institute For The Deaf | Electronic filter |
EP0448764A1 (en) * | 1990-03-30 | 1991-10-02 | Siemens Audiologische Technik GmbH | Programmable electrical hearing aid |
WO1997014266A2 (en) * | 1995-10-10 | 1997-04-17 | Audiologic, Inc. | Digital signal processing hearing aid with processing strategy selection |
Cited By (48)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7929723B2 (en) | 1997-01-13 | 2011-04-19 | Micro Ear Technology, Inc. | Portable system for programming hearing aids |
US6574342B1 (en) | 1998-03-17 | 2003-06-03 | Sonic Innovations, Inc. | Hearing aid fitting system |
EP1118249A1 (en) * | 1998-09-14 | 2001-07-25 | Micro Ear Technology, Inc. | System for programming hearing aids |
EP1118249A4 (en) * | 1998-09-14 | 2004-08-25 | Micro Ear Technology Inc | System for programming hearing aids |
WO2000016589A1 (en) * | 1998-09-17 | 2000-03-23 | Sonic Innovations, Inc. | Two line variable word length serial interface |
US6240193B1 (en) | 1998-09-17 | 2001-05-29 | Sonic Innovations, Inc. | Two line variable word length serial interface |
US6408318B1 (en) | 1999-04-05 | 2002-06-18 | Xiaoling Fang | Multiple stage decimation filter |
US7020297B2 (en) | 1999-09-21 | 2006-03-28 | Sonic Innovations, Inc. | Subband acoustic feedback cancellation in hearing aids |
US6480610B1 (en) | 1999-09-21 | 2002-11-12 | Sonic Innovations, Inc. | Subband acoustic feedback cancellation in hearing aids |
WO2001035695A3 (en) * | 1999-11-12 | 2002-01-24 | Siemens Hearing Instr Inc | Patient isolating programming interface for programming hearing aids |
WO2001035695A2 (en) * | 1999-11-12 | 2001-05-17 | Siemens Hearing Instruments, Inc. | Patient isolating programming interface for programming hearing aids |
US6757395B1 (en) | 2000-01-12 | 2004-06-29 | Sonic Innovations, Inc. | Noise reduction apparatus and method |
US9357317B2 (en) | 2000-01-20 | 2016-05-31 | Starkey Laboratories, Inc. | Hearing aid systems |
US9344817B2 (en) | 2000-01-20 | 2016-05-17 | Starkey Laboratories, Inc. | Hearing aid systems |
US6313773B1 (en) | 2000-01-26 | 2001-11-06 | Sonic Innovations, Inc. | Multiplierless interpolator for a delta-sigma digital to analog converter |
EP1196006A2 (en) * | 2000-10-03 | 2002-04-10 | FreeSystems Pte Ltd | On-demand audio entertainment device that allows wireless download content |
EP1196006A3 (en) * | 2000-10-03 | 2008-08-27 | FreeSystems Pte Ltd | On-demand audio entertainment device that allows wireless download content |
EP1250026A1 (en) * | 2001-04-11 | 2002-10-16 | Phonic Ear, Inc. | Short range data transfer for communication devices |
EP1410684B1 (en) * | 2001-06-28 | 2009-01-28 | Oticon A/S | Hearing aid fitting |
US8107657B2 (en) | 2002-07-12 | 2012-01-31 | Widex A/S | Hearing aid and a method for enhancing speech intelligibility |
EP1538873A3 (en) * | 2003-12-01 | 2010-01-13 | Siemens Audiologische Technik GmbH | Hearing aid with wireless transmission system and corresponding transmission method |
EP1538873A2 (en) * | 2003-12-01 | 2005-06-08 | Siemens Audiologische Technik GmbH | Hearing aid with wireless transmission system and corresponding transmission method |
US7433480B2 (en) | 2003-12-01 | 2008-10-07 | Siemens Audiologische Technik Gmbh | Hearing aid with wireless transmission system, and operating method therefor |
WO2005107319A1 (en) * | 2004-04-29 | 2005-11-10 | Jetta Company Limited | Digital noise filter system and related apparatus and method |
EP1694095A3 (en) * | 2005-02-15 | 2016-04-27 | Sivantos GmbH | Hearing aid with an output amplifier comprising a sigma-delta modulator |
DE102005016017A1 (en) * | 2005-04-07 | 2006-10-19 | Siemens Audiologische Technik Gmbh | Hearing aid device, has telephone coil utilized as antenna for high frequency signals above one mega Hertz, where evaluator is provided for evaluating high frequency signals of telephone coil |
US8224004B2 (en) | 2006-09-08 | 2012-07-17 | Phonak Ag | Programmable remote control |
US8300862B2 (en) | 2006-09-18 | 2012-10-30 | Starkey Kaboratories, Inc | Wireless interface for programming hearing assistance devices |
CN101611637A (en) * | 2006-12-21 | 2009-12-23 | Gn瑞声达A/S | Hearing device with user interface |
WO2008074323A3 (en) * | 2006-12-21 | 2008-08-07 | Gn Resound As | Hearing instrument with user interface |
US8165329B2 (en) | 2006-12-21 | 2012-04-24 | Gn Resound A/S | Hearing instrument with user interface |
CN105072552A (en) * | 2006-12-21 | 2015-11-18 | Gn瑞声达A/S | Hearing instrument with user interface |
DE102007018121B4 (en) * | 2007-04-16 | 2012-12-06 | Siemens Medical Instruments Pte. Ltd. | Hearing device with low-noise handset control and corresponding method and hearing system |
US8520881B2 (en) | 2007-04-16 | 2013-08-27 | Siemens Medical Instruments Pte. Ltd. | Hearing apparatus with low-interference receiver control and corresponding method |
EP1983800A3 (en) * | 2007-04-16 | 2009-10-28 | Siemens Medical Instruments Pte. Ltd. | Hearing device with highly reliable earpiece control and corresponding method |
DE102007018121A1 (en) * | 2007-04-16 | 2008-10-30 | Siemens Medical Instruments Pte. Ltd. | Hearing device with low-noise handset control and corresponding method |
US8638962B2 (en) | 2008-11-24 | 2014-01-28 | Oticon A/S | Method to reduce feedback in hearing aids |
EP2442590A3 (en) * | 2008-11-24 | 2012-10-24 | Oticon A/S | Method to reduce feed-back in hearing aids |
CN101917658A (en) * | 2008-11-24 | 2010-12-15 | 奥迪康有限公司 | Method to reduce feedback in hearing aids |
EP2190217A1 (en) * | 2008-11-24 | 2010-05-26 | Oticon A/S | Method to reduce feedback in hearing aids |
US8842863B2 (en) | 2009-04-06 | 2014-09-23 | Widex A/S | Two part hearing aid with databus connection |
US8532318B2 (en) | 2009-10-13 | 2013-09-10 | Panasonic Corporation | Hearing aid device |
WO2013001508A3 (en) * | 2011-06-29 | 2013-05-23 | Cochlear Limited | Systems, methods, and article of manufacture for configuring a hearing prosthesis |
US8855324B2 (en) | 2011-06-29 | 2014-10-07 | Cochlear Limited | Systems, methods, and article of manufacture for configuring a hearing prosthesis |
WO2013001508A2 (en) * | 2011-06-29 | 2013-01-03 | Cochlear Limited | Systems, methods, and article of manufacture for configuring a hearing prosthesis |
CN103491491A (en) * | 2013-09-22 | 2014-01-01 | 江苏贝泰福医疗科技有限公司 | Full-digital hearing aid and non-traditional hearing aid fitting method |
US11602632B2 (en) | 2014-09-30 | 2023-03-14 | Cochlear Limited | User interfaces of a hearing device |
US10225667B2 (en) | 2015-03-10 | 2019-03-05 | Sivantos Pte. Ltd. | Method and hearing aid for frequency-dependent reduction of noise in an input signal |
Also Published As
Publication number | Publication date |
---|---|
JPH10126895A (en) | 1998-05-15 |
CA2212131A1 (en) | 1998-02-07 |
EP0823829A3 (en) | 2000-01-26 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP0823829A2 (en) | Digital hearing aid system | |
EP0976302B1 (en) | Apparatus for and method of programming a digital hearing aid | |
AU610705B2 (en) | Auditory prosthesis with datalogging capability | |
AU579890B2 (en) | Hearing aids, signal supplying apparatus, systems for compensating hearing deficiencies, and methods | |
US6229900B1 (en) | Hearing aid including a programmable processor | |
JP2782475B2 (en) | Remotely controllable, especially programmable hearing aid system | |
US4791672A (en) | Wearable digital hearing aid and method for improving hearing ability | |
US7103108B1 (en) | Digital signal processor transceiver | |
US7949419B2 (en) | Method and system for controlling gain during multipath multi-rate audio processing | |
US5303306A (en) | Hearing aid with programmable remote and method of deriving settings for configuring the hearing aid | |
US6516073B1 (en) | Self-powered medical device | |
US8254606B2 (en) | Remote control of hearing assistance devices | |
US20110182444A1 (en) | Method and System for Handling the Processing of Bluetooth Data During Multi-Path Multi-Rate Audio Processing | |
CA2341255C (en) | Hearing aid with beam forming properties | |
JPH0640680B2 (en) | Programmable hearing aid system | |
US5319573A (en) | Method and apparatus for noise burst detection in a signal processor | |
KR20000005187A (en) | Method for automatically adjusting audio response for improved intelligibility | |
GB2184629A (en) | Compensation of hearing | |
CN206533360U (en) | Portable underwater digital handset communication system | |
EP0634845A2 (en) | Noise burst detection in an ADPCM decoder | |
US6718034B1 (en) | Headset interface | |
Staab | Digital/programmable hearing aids-an eye towards the future | |
CN1998265A (en) | Digital cell phone with hearing aid functionality | |
WO1999004487A1 (en) | Signal-processing device | |
US5937017A (en) | Complex signal limiting |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
PUAI | Public reference made under article 153(3) epc to a published international application that has entered the european phase |
Free format text: ORIGINAL CODE: 0009012 |
|
AK | Designated contracting states |
Kind code of ref document: A2 Designated state(s): AT BE CH DE DK ES FI FR GB GR IE IT LI LU MC NL PT SE |
|
PUAL | Search report despatched |
Free format text: ORIGINAL CODE: 0009013 |
|
AK | Designated contracting states |
Kind code of ref document: A3 Designated state(s): AT BE CH DE DK ES FI FR GB GR IE IT LI LU MC NL PT SE |
|
STAA | Information on the status of an ep patent application or granted ep patent |
Free format text: STATUS: THE APPLICATION IS DEEMED TO BE WITHDRAWN |
|
18D | Application deemed to be withdrawn |
Effective date: 20000301 |