JP2664466B2 - Hearing substitute device - Google Patents

Description

Description: TECHNICAL FIELD The present invention relates to a hearing aid device, and more particularly to a hearing aid having a data logging function.

(Prior art and its problems) Various types of hearing substitute devices are known and commercially available. These include hearing aids, spiral tube implants, implantable hearing aids, and vibrotactile devices.
One such substitute is a programmable hearing aid, which is described, for example, in US Pat. No. 4,425,481.
See issue No. The device has a programmable memory for controlling a signal processor that performs various audible signal processing. In said patent, the user can select one of several programs stored in a memory for processing signals by means of a manual program control means.

This conventional programmable hearing aid has various signal processing functions such as signal amplification, automatic gain control, filtering, and noise suppression. Therefore, a major problem is to select the value or set of values of the parameters that control the hearing aid in a manner that is most convenient for each user. Some users require extensive signal processing, while others require
It is better to use various programs for a more limited range of signal processing. Certain other conventional hearing aids are not programmable, but are user adjustable, and have similar range adjustment limits.

SUMMARY OF THE INVENTION In summary, according to a preferred embodiment of the present invention, a programmable or manually adjustable hearing aid
Alternatively, a data logging function is provided in a memory attached thereto. The memory records or logs user-selected events, such as set values, parameters, or algorithms, the number of times a given set value was selected, and the change in the time the given set value lasts. Things. The memory may also include environmentally selected events, such as settings, parameters, or algorithms, if the selection is based on calculations made automatically in response to the wearer's current acoustic environment. May be recorded. In a preferred embodiment,
The method to determine the value of each data log is approximately 2 minutes (128
(Seconds). The duration of each set point is then recorded in units of 2 minutes. In a preferred embodiment,
Individual program settings are not recorded until the time period given for each set value has elapsed, so that the user may need to set many settings while examining the various settings to obtain the desired response characteristics. There is no need to record.

The control device could be integrated with the processing device of the hearing aid or could be external to the processing device. However, in a preferred embodiment of the programmable hearing aid, the control device is remote from the hearing aid processing device and includes a transmitter (eg, acoustic, electromagnetic, or infrared) that sends control signals to the processing device. have. The data log memory can be located in the ear portion of the hearing aid or in the control device. With a remote control with built-in datalog memory, the ears are smaller, lighter and less noticeable.

When the user returns the hearing aid to the container, the hearing aid can be reprogrammed or re-adjusted appropriately, taking into account the information in the data log. The container reads out the data recorded in the data log memory using an appropriate connection to the hearing aid. Based on this information, a new set of operating parameters can be programmed for the user. It interprets how much the user used the original program and selects a new program based on that interpretation.

For example, consider a method of performing initial programming by giving a continuum including volume, noise suppression, and gradually increasing intelligibility to a memory. If all programs are used equally, the programming can be deemed appropriate. However, if all the programs were used, but the signal processing method at the end of the programmed range is used more frequently than in the central region, it should spread to that parameter range. Also, if a program in the central area of signal processing is mainly used, the scope of the program should be reduced so that the user can select more finely the settings that he finds most useful. . In particular, it can be seen that other reprogramming schemes are possible as well as other initial programming schemes.

In this document, the word "program" refers to any one of setting a limited number of parameters, selecting a processing method, partially modifying a proxy device control program, or setting a coefficient in a proxy device program. And

The nature of the invention, as well as other objects and features, will be more readily understood from the following description and appended claims, taken in conjunction with the accompanying drawings.

FIG. 1 is a functional block diagram of a multiple memory programmable hearing aid 2 described in U.S. Pat. No. 4,425,481 (which is incorporated herein by reference). The hearing aid 2 has a microphone 10 for picking up sound and converting it into an electric signal, and a signal processing device having an attached slave memory 12 acting on the electric signal generated by the microphone 10 according to one of a plurality of signal processing programs. It includes a device and a speaker 14 for audibly transmitting the processed signal. Other signal inputs, such as telecoils, can also be provided. The programmable memory with logic 16 stores a plurality of programs for controlling a signal processing device that operates on a signal from the microphone 10.
A hand-operated program control switch 18 is provided for use by a user to select from several programs stored in memory 16.

As mentioned above, this conventional programmable hearing aid
It has a wide range of signal processing functions, including signal amplification, automatic gain control, filtering, and noise suppression. Therefore, the main problem is to optimize the programming of the hearing aid so that each user is easiest to use.

FIG. 2 is a functional block diagram of a programmable hearing aid 4 with a data logging function according to one embodiment of the present invention. This hearing aid also has microphone 10, slave memory
12 and a speaker 12. However, according to the present invention, the programmable memory with logic 20 further has a data logging function. A programmable decoder 22 is connected to the programmable memory 20. The decoder is responsive to an encoded digital control signal received by the microphone 10 and transmitted from the loudspeaker of the remote control of FIG. 3, described below. The carrier frequency of this control signal is in the upper part of the microphone bandwidth and is inaudible to the hearing aid user.

FIG. 3 is a functional block diagram of the remote control device 6, which can be attached to, for example, a user's pocket or wrist. The remote control device 6 is a manual program control device 24
And the logical block that interfaces with the transmit coder 28
26 and. The encoder and decoder of the hearing instrument are programmed with the same ID number included in the control signal so as not to affect other similar hearing instruments. The transmitter is connected to the speaker 30 and transmits the coded instructions to the hearing aid, spiral tube implant, or implanted hearing aid of FIG. 2, 3, or 4. Automatic program selection device (APS)
Can automatically select a program according to the ambient noise level detected by the program. In one embodiment, the APS goes through each program in the programmable block 26 and stops at a program in which the ambient sound level has been increased above a certain (manually adjustable) level. Next, the program number is sent to a programmable substitute device worn on the head, where the program is input.

In another embodiment, a calculation is made using the sound level and spectrum measured by the microphone 32 to determine the value of each of the parameters that make up the program, and then those parameters are passed through the coder 28 and speaker 30. To the proxy device through a transmission medium (acoustic medium, infrared medium, electromagnetic medium, etc.).

In a preferred embodiment of the invention, the data logging means records the number of times the set value has changed, the number of times the given set value has been selected, and the duration for which the given set value has been selected. A practical way to determine the value of each of these quantities is to count for as long as about two minutes (128 seconds). Therefore, the duration is recorded in units of 2 minutes. In addition, the set value is not recorded until the given time elapses for the given time, which saves the user from having to record the set value while simply checking the set value.

4 and 5 are functional block diagrams of a hearing aid 8 and a remote control device 9 according to another embodiment of the present invention, respectively. This embodiment is similar to the embodiment of FIGS. 2 and 3 and similar elements are given the same reference numerals. The main difference between the two embodiments is the logic and data logging functions. That is, the programmable memory 20 with the tag is removed from the hearing aid of FIG. 2, and the function of the memory 20 in the programmable APS device 26 with the logic is given to the remote control device 9 of FIG. Eliminating the data logging function from the hearing aid reduces the size and weight of the hearing aid. Further, a remote control having a larger size and greater battery power can be provided with more advanced programmable memory and data logging capabilities.

While the invention has been described with reference to the remotely controlled programmable hearing aid of the embodiment of FIGS. 2-5, the invention is not limited to the manually adjustable, unprogrammed hearing aid or the spiral tube shown schematically in FIG. It can also be performed on implants. In this embodiment, a hand-operated control device
29 is connected to a signal processing device 33 by a wire 31. The data logging device 35 includes a memory means for monitoring the control selecting device 29 and recording the usage time of a plurality of options. The device 35 is read from the output 37 periodically. Output 39
Is, for example, U.S. Pat.No. 4,357,497 or U.S. Pat.
No. 9,995, which is incorporated herein by reference, and which may be comprised of acoustic speakers or spiral tube implants. Finally, the present invention can be used in a substitute device in which the operation mode is automatically switched. In this case, the validity of the decision algorithm used to perform the automatic switching or adjustment is monitored using the data logging information.

In this document, the term "program" refers to a specific set value of a limited number of parameters; selection of a substitute device form or processing method in a substitute device designed to be able to select a plurality of processing modes; Selection of an algorithm or a form of an algorithmic microprocessor or a set of microprocessor instructions; or microprocessor-controlled instructions, such as changing the number and value of filter coefficients in a digitally controlled or digitally executed filter (eg, a FIR or IIR filter) Should be understood to refer to any of the set of constants or coefficients.

7A, 7B, and 7C are more detailed functional block diagrams of the programmable hearing aid 4 with the data logging mechanism shown in FIG. This embodiment is incorporated in two integrated circuits 36, 38 having circuit terminals indicated by square symbols. The integrated circuit 36 (FIG. 7A) comprises a memory 42 which transfers a part of the stored information via a line 41 to a slave memory 82 of the analog signal processor of FIG. 7B. The integrated circuit 36 includes a voltage doubler (charge pump),
And an analog block 40 containing an external crystal controlled oscillator controlled at 32, 768 MHz. When the device is turned on, the negative pole of the power battery is connected to ground and the oscillator is started with the help of a support battery. The oscillator starts the voltage multiplier, which generates a negative voltage VSS at the voltage multiplier and buffer-capacitor. When the device is turned off, the voltage level detector is activated and the support battery is reconnected to protect the data in RAM.

RAM 24 consists of a total of 896 bits organized into 118 × 8 bits. The 112 groups of bits for each listening state are divided into 64 bits for slave memory, 4 bits for telecoil control, and 24 bits for data logging.

The RAM area is programmed and / or read by an external programming device using the serial channel block 44. Data can be written to or read from the hearing aid via the serial line connection 111. The timing program 64 constantly monitors the timing for the various blocks, transfers data, and generates clock pulses to the slave memory. The input test block 48 controls the activity of the external switch and the power reset pulse from the analog block.

The data logging block 50 provides logic to the RAM 42, which includes two data logging registers of 12 bits each for each program setting. The first register is incremented each time the listening condition is used for more than two minutes. The second register is incremented every fourth minute while the listening state is being used.

Another 24-bit register is incremented after switch 90 is activated.

The signal processor of FIG. 7B has a microphone input 52, a telecoil input 54, and a sound input 56. The telecoil and microphone inputs are preamplifiers (PREAMP)
The signals are passed through 58 and 60 and digitally controlled attenuators (DCAs) 59 and 61 and summed with the acoustic input signal in the SUM unit 62. The output from device 62 is sent via line 63 to a filter 64 (FIG. 7C), which splits the signal into a low-pass signal and a high-pass signal. The crossover frequency between the low-pass channel and the high-pass channel can be digitally changed from 500 Hz to 4 KHz.

The low pass filter 65 and the high pass filter 67 are identical and comprise an automatic gain control amplifier (AGC). The recovery time of the FGC is soft clipping (ie,
The low band signal and the high band signal are summed at 66 via digital attenuators 68 and 70, which can be controlled to obtain short, normal, and long recovery times.

An output amplifier 72 is provided to receive the output summed at 66 and drive the converter 742. Also, an external output amplifier that performs this driving function can be used.

The digital portion of chip 38 includes logic circuit 80 and slave memory 82 (FIG. 7B). Slave memory
Numeral 82 denotes a 55-bit non-resettable shift register, into which data is serially fed into the register at each positive clock transition. Information in the slave memory controls various functions in the analog circuit.

A 64-bit data word is loaded into the slave memory with 64 clock pulses.

As mentioned above, the data logging logic performs three logic functions. First, it records the total number of times new data is sent to the device. A total of 24 bits are available in this register (16,777,215 events). This locking function is referred to as the data log total (DL
S). The second function of the data logging circuit is:
To record the number of times a particular register is used for more than 128 seconds (2.13 minutes). There are 12 bits in each of the eight registers used for this type of record (4095 events).
This recording function is referred to as data log A (DLA) in this document. The third function is to record the number of times each particular register has been activated. Each time count is equal to 256 seconds (4.27 minutes). Again, there are 12 bits in each of the eight registers (about 291 hours). This recording function is referred to as data log B (DLB) in this document. The actual increment of the register is performed in the data buffer portion of the RAM block.

FIGS. 8-13 show the circuit of FIG. 7B performing the data recording function in more detail. Although this implementation is performed by hard wiring, it will be appreciated that the functions of the circuit may be performed, for example, by a programmed microprocessor. In FIG. 8, since the data logging recording and holding circuit has an UP button and a DOWN button 90 for counting up and counting down the 8-bit counter 91, only one of the eight outputs B0-B7 is always active (high). ). When this output changes to a new value and is stable, the DELTA () output will generate a pulse called a memory select load.

Each time a memory select load (MSL) pulse is generated, this causes the DLS counter 92 to increment, which is the number of switching events. At this time, the 22-stage frequency divider 93 and the frequency-divided-by-2 flip-flop 94 are also reset to zero. The MSL pulse sets RS flip-flop 95, which allows loading of DLA register-98.

When the frequency dividers 93 and 94 are reset, the self-excited 32768 Hz crystal oscillator 96 causes the frequency divider 93 to start counting up. When the frequency divider 93 counts ²²² , its output becomes HIGH, which is 128 seconds after the MSL pulse is generated.

The output of the 22-stage divider 93 outputs a pulse which is one of the selectively connected bits B0-B7 of the up / down counter 91 and the RS set by the MSL.
An AND operation is performed on the Q output of the flip-flop 95. As a result, the DLA register 98 is incremented. Since the change in the input to the KLA register is used to reset the RS flip-flop 95, the DLA register is incremented by 1 for each change of the 8-bit up / down counter, and the divider 93 is provided. This increment occurs only if the state of the counter is held constant for more than two minutes.

When the output of the 22-stage frequency divider 93 is divided by 2 by the divide-by-2 FF94, the result is that the associated DLB register 99 is updated every 256 seconds when the bits B0-B7 attached to the up / down counter are selected. Used to increment.

Also, all registers can be provided with RS flip-flops (identified by prime numbers), which are set each time the associated register overflows.

In this way, the data read from the hearing aid is
Even if the usage time exceeds 256 × 2 ¹² seconds, it can be interpreted.

The hearing aid communicates with the outside world through a serial interface 100 shown in FIG. This communication is governed by ordinary logic, which detects an appropriate command from the programmer to load into the hearing aid or a command to send information about the hearing aid settings or data logging information back to the programmer. I do. Also, the access code is checked with input from the programmer to prevent the hearing aid program from being accidentally changed.

The data of the selected register 102 passes through the shift register 101. This is the data logging information (DLS,
DLA and DLB registers), global programming information (eg, number of active memories), and individual parameter registers 102 (for memories 0-7) can be read or written.

When the MSL pulse is generated, the contents of the appropriate parameter register 102 (selected by B0-B7) are loaded into the second shift register 103, which then stores the data in the analog integrated circuit 38 (FIG. 7B). Serially clocked and loaded into the slave memory 82.

Appropriate circuits can be modified so that the functions of the shift register and the storage register are performed by the same circuit, but the logic circuit and analog hearing aid circuit such as those shown in the aforementioned U.S. Pat. No. 4,425,481. The operation is shown in FIG. 9 to clarify the details of the communication between and. Functionally the circuit works as described above,
There may be one large RAM random access memory structure, there should be no separate data registers, and there may be a single 16-bit shift register that acts as the heart of transmission and reception with digital control circuits.

The internal RAM on the digital circuit 36 is arranged in an XY matrix, as shown in FIG. When memory is selected, the value Y from 0 to 7 is set in RAM,
A special function, such as loading memory into the analog circuit 38 or incrementing the data logging registers 92, 98 or 99 (FIG. 8), causes the X value used in the current operation (ie, the particular value of the matrix to be used). 16-bit cell) is selected. Random access memory 104 (first
1) is maintained by continuously applying the backup voltage. This is the only voltage maintained when the hearing aid is not actively used. When a standard 1.3V hearing aid battery 127 is in the hearing aid, the backup voltage is obtained via a voltage multiplier 119 (required due to the characteristics of the integrated circuit process used). When the ordinary 1.3V battery 127 is removed, the minimum current required to prevent memory changes is provided by the internal 3.1V lithium battery.

The RAM 104 is actually divided into a 64-bit parameter field 105 for each memory and a 48-bit field for data logging. The configuration of the data logging area is
This is shown in more detail in the RAM layout diagram (FIG. 11).

At the heart of the logic function that supports the programmable hearing aid is the 16-bit register 110 shown in FIG. 12, which acts as a serial input / parallel output register for incoming data; Or acting as a parallel input / serial output register for reading the RAM back to the host; acting as a parallel output / parallel input incrementing register for data logging recording. Communication functions (host programming, hearing aid programming, and data readback) are controlled upon receipt of the appropriate code.

The action of programming the hearing aid The preamble access code is the access control block
After being checked by 115 and successfully received from the host, the serial input / output control circuit 116 resets the address counter 112 and clocks in data 16 bits at a time via the serial line 111. Each one
When the six bits are accumulated, they are transferred to RAM memory 104. This process continues until the entire memory is rewritten.

Action of reading the hearing aid When a read access code is received from the host,
The serial input / output control circuit 116 has an address counter 112
To move the 16 bits into the shift register 110 and begin clocking them out of the serial line 111. This process continues until the entire contents of the memory 104 has been sent over the serial line 111.

Function of setting analog circuit When a new memory is selected, the Y register 113
Is changed to reflect another memory selected. X register 112 is set to zero, and four consecutive 16-bit words are loaded into shift register 110 and the effect of being shunted out to analog circuit 38 via line 114 begins. Thus, the 64-bit programming information is sent to the analog chip 38.

Action of Incrementing Data Logging Bit An outline of the action is described in the basic structure of FIG. Each time the active memory is changed manually or automatically, this will: (1) generate an interrupt, reset the 23-stage counters 93 and 94, (2) change the addresses of the logic circuits 112 and 113, (3) Extract the value of DLSa, (4) DLSa
Is incremented, and (5) DLSa is returned to the memory 104. (6) If step 4 overflows, (12)
If the count exceeds the number of bits), DLSb is 3,
Repeat steps 4 and 5, (7) set the latch, and
And DLB can be incremented with future clock pulses. If the active memory is changed after 128 seconds, the memory select load has not been pulsed again, and a positive transition from the outputs of the 23-stage counters 93 and 94 causes an increment cycle in the DLA:
(1) Take out DLA, (2) Increment,
(3) Return to memory. Subsequent positive going cycles of counters 93 and 94 cause the DLB to be similarly incremented.

Thus, the counting operation performed is as follows:
(A) Each time the memory is changed from one memory to another, the DLSa (LSB) and DLSb (MSB) are incremented immediately, and after the first 128 seconds have elapsed in the same memory, the DLA
Is incremented once, and (c) the DLB is incremented every 256 seconds after the DLA increment. This means that the first increment of the DLB is made 128 + 256 seconds after the memory change. This structure is implemented using positive going transitions at the outputs of the 23-bit counters 93 and 94, where the first positive going transition occurs 128 seconds after reset, but the period of the counter is actually Between the positive transition and the positive transition
It is configured to be 256 seconds.

Increment logic is a 16-bit shift register
Part of 110. The increment is performed by adding the twelve half addresses to the twelve least significant bits (LSB) of the shift register of the incrementer 117. Carry register 118 is used in the DLS calculation to generate a second increment cycle for the DLAb if necessary.

In the configuration of the data logging area of the RAM, the devices 112 and 11
The address generation of DLSa and DLSb at 3 is to sense the exception condition and temporarily redirect the Y register 113 to the appropriate registers for memories 0 and 1, and redirect the X register 112 to the last word in these registers. Promoted by

As described above, the user returns the hearing aid to the container after using the hearing aid for a certain period of time. The container then reads the data stored in the data logging information memory using the appropriate connection to the hearing aid. With this information, a new set of programs can be stored in memory for the user. The choice of the new program depends on how much the original program has been used.

Obviously, the concept of data logging depends on the ability to provide multiple settings for the hearing aid and to record the duration of those settings. This information can be adapted to the memory in the proxy device memory controlled by the remote control source or to the memory in the remote control source, in which case the data logging means is built into the remote control source It is useful to have been.

Data logging information can be used not only to modify the hearing prescription of personal devices, but also to refine the initial prescription of future patients whose tensile properties resemble that of the user. .

While the invention has been described with reference to a particular embodiment,
This description is an illustration of the invention and should not be construed as limiting the invention. Those skilled in the art will appreciate that various modifications and uses can be made without departing from the true spirit and scope of the invention as defined in the following claims.

[Brief description of the drawings]

FIG. 1 is a functional block diagram of a programmable hearing aid device according to the prior art. FIG. 2 is a functional block diagram of a remotely controlled programmable auditory substitute device having a data logging function according to an embodiment of the present invention. FIG. 3 is a functional block diagram of a remote control device used for the hearing substitute device of FIGS. 3 and 2. FIG. 4 is a functional block diagram of a remotely controlled programmable hearing aid device according to another embodiment of the present invention. FIG. 5 is a functional block diagram of a remote control device having a data logging function used in the hearing substitute device of FIG. FIG. 6 is a functional block diagram of an unprogrammed auditory substitute which is manually adjustable and is another embodiment of the present invention. 7A, 7B, and 7C are detailed functional block diagrams of the programmable hearing aid device of FIG. FIG. 8 to FIG. 13 are functional block diagrams showing the operation of data logging in the hearing aid device. 6 Remote control device 10, 32 Microphone (signal input means) 20 Programmable memory 22 Programmable decoder 4 Programmable hearing aid 14, 30 Speaker

Claims (10)

(57) [Claims] 1. Signal input means for providing an electric signal representing an audio signal, signal processing means connected to receive the electric signal, and processing the electric signal according to a control program, and acting on the signal processing means. Memory means for storing a plurality of control programs for controlling the signal processing means, and operatively connected to the programmable memory means for allowing a user to select a control program And a converter connected to the signal processing unit and receiving the processed electric signal. A programmable auditory substitute device comprising: the programmable memory unit and the control unit. Operatively connected to the user to select a control program and to select the selected control program. A data logging means for recording the use period, the connected to the data logging means, a programmable hearing proxy device, characterized in that it comprises, means for reading the data logging means. 2. The apparatus according to claim 1, wherein said control means is connected to said signal processing means from a remote place, and said control means includes signal transmission means for transmitting a control signal to said signal processing means. A programmable hearing aid device as described. 3. The control signal is transmitted as an audio signal,
3. The programmable hearing aid device according to claim 2, wherein the signal input unit includes a microphone for receiving the control signal. 4. The programmable hearing aid according to claim 2, wherein said programmable memory means and said data logging means are located in said control means. 5. The programmable hearing aid device according to claim 2, wherein said programmable memory means and said data logging means are electrically connected to said signal processing means. 6. The control means includes: microphone means for receiving an audio signal; and automatic program selection means for automatically selecting a control program according to characteristics of the audio signal received by the microphone means. The programmable auditory substitute device according to claim 2. 7. The data logging means comprises: a total number of times the control program for the signal processing means has been changed; a number of times each control program has been used at least for a minimum period; and a total number of times each control program has been used. 7. The programmable auditory substitute device according to claim 6, wherein 8. The programmable auditory substitute device according to claim 7, wherein each control program controls amplification of an electric signal, noise suppression, and improvement of clarity by the signal processing means. 9. A hearing aid device that can be adjusted in a plurality of processing modes, comprising: signal processing means for providing an electrical signal representing an audio signal; operatively connected to receive the electrical signal; A signal processing means for processing the electrical signal according to a selected one of the plurality of processing modes; operatively connected to the signal processing means; A control means operated by one of them, a data logging means connected to the control means, and recording a selection of the plurality of processing operation modes; and a data logging means operatively connected to the data logging means. Means for reading the recorded selection, and converter means connected to the signal processing means for generating an electric signal in accordance with the processed electric signal. Hearing substitute equipment, characterized in that it consists. 10. The hearing substitute device according to claim 9, further comprising a memory for storing a record of the selection of the plurality of processing operation modes and a use period of the processing operation modes. .