JP2005531175A - Programmable hearing prosthesis that can automatically adapt to the acoustic environment - Google Patents

Abstract

The hearing prosthesis (30) receives sound, generates a microphone signal corresponding to the received sound, an output device that provides the sound signal in a form that can be received by the user, and the microphone signal. An acoustic processing unit (33) for receiving and processing and generating an output signal in a form suitable for the operation of the output device,
The acoustic processing unit (33) is operable in a first mode, in which the output signal of the acoustic processing means can be adjusted according to the user's preference for current acoustic environmental characteristics. And including at least one variable processing factor that can be adjusted by the user.

Description

  The present invention relates to programmable hearing prostheses such as hearing aids or artificial ears. In particular, the present invention relates to a programmable hearing prosthesis that is tuned to adapt to the environment in a similar or identical manner to the acoustic processing characteristics when the user has already adapted to the environment in a special acoustic environment.

  Hearing loss is caused by many different causes, which can be divided into those resulting from abnormal auditory conduction and those resulting from abnormal sensory nerves. Of these, the loss of auditory conduction is due to the fact that the normal mechanical pathways for sound reaching the hair cells in the cochlea are hindered, for example, by damage to the small bones. Auditory conduction loss can be compensated by using conventional hearing aids. The hearing aid includes a microphone, an amplifier, and a receiver (small speaker) so that acoustic information can reach the cochlea and hair cells. Since the minimum audible acoustic pressure level varies with the frequency of the acoustic test stimulus, the amplifier is placed in front of a group of filters arranged in rows so that different frequency components of the signal are amplified to different levels. Or configured to include the filter group.

  Sensory nerve abnormalities occur when hair cells and associated auditory nerve networks in the cochlea are damaged or destroyed. As sensory nerves become abnormal, the minimum audible acoustic pressure level increases. As mentioned above, the minimum audible acoustic pressure level varies with the frequency of the acoustic test stimulus. However, in contrast to auditory conduction abnormalities, the sound pressure level that feels uncomfortable at a given test frequency is often the same as people with normal hearing ability. This is because the dynamic range of the acoustic pressure level of the non-disabling audible range of a non-functional ear is decreasing, said dynamic range changing dramatically with the frequency of the acoustic test stimulus. For these reasons, sensory nerve abnormalities are frequently dealt with by using hearing aids that utilize non-linear amplification to compress the general dynamic range to a non-functional ear dynamic range. Such a system has a filter bank behind the pressure amplifier. As a result, the dynamic range of the signal is reduced to a predetermined range that appropriately takes into account the dynamic range of the non-functional ear in each band.

  In many people who are deaf at all, the hearing loss is due to hair cell loss or damage in the cochlea that transmits acoustic signals to nerve impulses. Thus, no matter how much the acoustic stimulus is amplified, these people have their symptoms improved sufficiently by using hearing aids because of the disruption or loss of the nerve impulse mechanism that normally results from sound. It will not be done. In view of this situation, hearing prostheses have been developed. The auditory prosthesis bypasses hair cells in the cochlea and transmits electrical stimuli directly to the auditory nerve network, allowing the brain to accept hearing similar to natural hearing normally transmitted to the auditory nerve. ing. USP 4,532,930 discloses a traditional hearing prosthesis. The contents of the US patent are included in the present specification as references.

  A hearing prosthesis typically includes two essential elements. One is an external component as a processor unit and the other is an implant component as a stimulator / receiver. Traditionally, these two components cooperate to provide an acoustic sensation to the user.

  The external component has traditionally been a microphone for receiving sound, such as speech and environmental sound, a speech processor that converts received sound, particularly speech, etc. into a coded signal, a power source such as a battery, and an external transmitter coil It is composed of

  The coded signal output from the speech processor is transmitted percutaneously to an implant stimulator / receiver unit located in a portion of the user's temporal bone. This transmission takes place via an external transmitter coil, which is located so as to be connected to an implant receiving coil provided in the implant stimulator / receiver unit. Such a transmission takes place for two essential purposes. One is for transcutaneously transmitting the coded acoustic signal and the other is for providing power to the implant stimulator / receiver unit. Traditionally, such links have been made in the form of RF links, and other links have been proposed and implemented with varying degrees of success.

  The implant stimulator / receiver unit traditionally receives the coded signal, receives the power from the external processor unit, and processes the coded signal to produce the original received sound. And an internal auditory electrode assembly that provides electrical stimulation directly to the auditory nerve that produces the auditory equivalent of a stimulator that outputs a stimulation signal.

  The user requests the auditory prosthesis to output different stimulation signals according to individual request levels. This situation occurs even when individual users have the same hearing abnormality and use the same prosthesis, and also when placed in essentially the same acoustic environment. In view of these problems, acoustic processing schemes for hearing aids and prosthetic organs have many parameters that are set to meet the needs of individual users. For example, sensitivity to input sound and variation to frequency response. Typically, these parameters are selected by the user in day-to-day situations or by the clinician attaching the prosthesis. In the former case, for example, sensitivity (volume), frequency response, and the like are parameters to be selected. In the latter case, for example, the frequency response and the speed of change in sensitivity that change based on changes in the baseline frequency response and input level. .

  Particularly recently, there is a tendency for auditory prostheses to increase the number of parameters that should be adjusted or can be adjusted to match the desired performance. However, even if the number of parameters increases in this way, this results in the problem that there is no reliable normative method for selecting the optimum parameter value for each user. Some of them are prominent when they vary between individuals with identical hearing impairments. Therefore, it is necessary for the clinician to be able to adjust the prosthesis based on the user's reported experience outside the actual clinic, and the time that he must return to the clinic for the adjustment It is also necessary to eliminate waste and inconvenience.

  An example of a hearing aid from which a hearing aid user can obtain hearing is disclosed in USP 5,604,812. The hearing aid also takes into account the actual driving method, “unsharp inputs”, ie general environmental conditions and / or hearing aid output values, prescribed algorithms, hearing loss data, and hearing aid characteristics data. It has a memory that can store the “sense” of the hearing aid wearer. The fuzzy logic module uses the data to control the signal from the input signal analysis unit and calculate the output parameters for the hearing aid. The fuzzy logic circuit module and / or the algorithm performs calculations based on data stored in auxiliary memory by a neural network. During this time, the neural network is driven in a personal computer connected to the auxiliary memory. Such hearing aids have the problem of complicated processing schemes and the problem of undesirably large current drain in auxiliary power supplies, typically on-board batteries. In addition, the hearing aid takes a long time to drive accurately, making it difficult for the user to set the optimal state directly, which is rather necessary for the hearing aid more accurately and directly. It is preferable to perform “unsharp input” rather than input.

  Another example of a hearing aid that allows a hearing aid user to receive hearing is disclosed in USP 6,305,050. According to this hearing aid, the user is required to identify the current acoustic environment by selecting one of the acoustic conditions in the remote unit. In this case, since the user cannot instantaneously determine the current acoustic condition from the selected acoustic condition, the advantage of the hearing aid is greatly reduced. In addition to these problems, remote units, such as active remote units, will have different acoustic environments, and as a result, acoustic conditions may not be well defined. Therefore, the neural network may not be able to fully recognize the acoustic situation from the analysis of the microphone signal. The acoustic situation is preferably recognized within a few seconds to several minutes from the practical viewpoint that it is preferable to recognize the memory limit and the change in the acoustic situation at an early stage. Therefore, even after the predetermined training is performed, the neural network may possibly recognize the acoustic situation erroneously. This is especially true in situations where acoustics cannot be well defined. As a result, the amplification parameters are not suitable for the current acoustic situation. In such devices, attempts have been made to classify specific acoustic environments instead of measuring environmental parameters or using these parameters directly in the processing scheme. This is a technical matter common to the present invention. The device also requires different amplification parameters due to changes in the living environment, such as a new work place that is acoustically different from the previous work place, and as a result, has to go to the clinic again.

  Hearing aids can also accept the preferences of their users, and such hearing aids are described in USP 6,044,163. The hearing aids described in this document are similar to those described in USP 6,035,05, but the main difference is that the neural network selects the amplification parameters stored in memory collectively. Without setting individual amplification parameters directly. The other disadvantages of the hearing aid are the same as in the hearing aid described in USP 6,035,050.

  It is an object of the present invention to provide the user with an auditory prosthesis that is adjustable and can adjust the output state for the user when placed in a variable acoustic environment.

  In addition, the present invention optimizes the sound of the user by adjusting the output state so as to suit the user's preference even in the sound situation encountered by training of individual users away from the traditional medical environment. Therefore, an object of the present invention is to provide the user with a hearing prosthesis that can shorten the medical examination time required.

  Documents, operations, materials, devices, parts, etc. included in this specification are required to achieve the objectives of the present invention. Some or all of these elements constitute prior art or known art in the field related to the present invention and do not exist before the priority date related to the claims of the present application.

Means for Solving the Invention

In order to achieve the above object, the present invention provides:
A microphone that receives sound and generates a microphone signal corresponding to the received sound;
An output device that provides an acoustic signal in a form receivable by a user;
Acoustic processing means for receiving and processing the microphone signal and generating an output signal in a form suitable for operation of the output device;
Data memory means for storing the setting state;
The acoustic processing means is operable in a first mode, in which the output signal of the acoustic processing means can be adjusted according to a user preference for current acoustic environmental characteristics. Including at least one variable processing factor that can be adjusted by the user,
The acoustic processing means is operable in a second mode, and the at least one variable processing factor is automatically adjusted based on a variable processing factor previously adjusted by the user;
The data memory means relates to an auditory prosthesis (first auditory prosthesis) that stores the setting state in the first mode.

  In the present invention, it should be understood that what is considered as an optimal output signal for one user is not considered as an optimal signal for other users. The present invention relates to the hearing prosthesis in a method that meets the user's requirements rather than a method predetermined by a medical examination when the user is in contact with an acoustic environment that is different from the acoustic environment that is routinely or occasionally in contact with the user. Is guaranteed to drive. Note that the acoustic environment does not necessarily cause the user to repeat subjective reactions when the user touches.

  Preferably, the data memory means stores a data set representative of at least one acoustic environmental characteristic. Preferably, the at least one variable processing factor is automatically adjusted based on an acoustic environment corresponding to the factor.

  In a first aspect, when operating in the first mode, the acoustic processing means provides two or more optimal setting states of the at least one variable processing factor selected by the user. In this case, the user can compare the driving state of the hearing prosthesis when driven in a specific acoustic environment with the driving state in each setting state, and from these setting states to the acoustic environment. The best matching setting state can be selected. The setting state of the variable processing factor selected by the user can be stored in the data memory means together with the data indicating the acoustic environment characteristics as necessary. This process is repeated so that the processing means can monitor whether the user's preference for the setting state of the variable processing factor changes over time or over time.

  When repeating the process as described above, the number of selections made by the user for each setting state is monitored, and the hearing prosthesis is optimized for the variable processing factor setting, or, if necessary, for a particular acoustic environment. It becomes possible to select the optimum setting state of the variable processing state.

  In this example, the user can change the listening environment based on the provided setting state by driving the control means, and select the setting state of the variable processing factor by operating the indicator means. can do. In one example, the control means may comprise a switch or button group operable by a user, and the indicator means may comprise a switch or button group operable by the user.

  In another example, the acoustic processing means may be adjustable when the acoustic processing means is driven in a first mode. In this case, the user can change the variable processing factor in a substantially continuous range by adjusting the control means instead of discontinuously selecting the optimal setting state, and thus processing. The operation can be changed. When the user adjusts the control means to a predetermined setting state within the substantially continuous range, which the user thinks is an optimal setting state for a specific acoustic environment, the user may indicate an indicator such as a switch or button. By operating means, data indicating the setting state and, if necessary, the specific acoustic environment is stored in the data memory means. When the indicator means is driven by the acoustic processing means, the indicator means indicates that a particular setting state in the control means is optimal for the particular acoustic environment.

  In this example, the control means may comprise a rotary wheel control. The rotary wheel control can be mounted on the hearing prosthesis housing or on a remote unit. The control means may be in the form of a toggle switch or a press button.

In the example described above, the indicator means can be mounted on the housing of the hearing prosthesis or on a remote unit.
In a preferred embodiment, the setting state selected by the user as optimal for a plurality of acoustic environments may be stored in the data memory means together with data indicating the acoustic environment characteristics, if necessary. it can. The acoustic processing means can be driven in the second mode, and for a predetermined time or a new setting state that the user adjusts the control means to consider optimum for a specific acoustic environment. Each time it is selected, it can be driven simultaneously in the first mode. In another example, the hearing prosthesis can determine a time to drive in the first mode. This time can be set as desired by the user. After the training time is complete, the hearing prosthesis can signal the user. In this case, in the auditory prosthesis, the end of the training time can be ended when it becomes impossible to select a setting state different from the setting state already evaluated by the auditory prosthesis.

  In a preferred aspect of the present invention, the hearing prosthesis may further include acoustic analysis means. The acoustic analysis means receives an input signal from the microphone and monitors the acoustic environment of the user. The acoustic analysis means provides an output representative of the monitored acoustic environment.

  Furthermore, the data memory means may comprise one or more data memory locations. For example, the data memory means can comprise five data memory locations. In this example, the first data memory location includes user hearing data and / or individual data for one or more sounds used by the hearing prosthesis. The second data memory location contains characteristic data of the hearing prosthesis. The third data memory location comprises one or more formulas used by individual users to anticipate optimal processing operations of the acoustic processor unit in different acoustic environments. The fourth data memory location stores the optimal acoustic processing data selected by the user. This data can be ordered sequentially or in different ways to indicate the acoustic environment data supplied by the acoustic analysis means. The acoustic environment data corresponding to the optimal acoustic processing data can be stored in the fifth data memory location as appropriate. It is also possible to use data memory means having different memory locations.

  The fourth data memory location may store a pre-defined maximum number of optimal acoustic processing data. For example, 400 optimal acoustic processing data can be stored. However, the maximum value may be another value. For example, the data processing means does not use all the accumulated data, but also uses a predetermined number of recently recorded data. For example, when determining the optimum value of the variable processing factor, only the latest 256 data can be used. Also, the newest data can be stored in place of the oldest data in the memory location. This first-in first-out storage system can arbitrarily store data recorded recently in the hearing prosthesis. In addition, when the memory location is full, old data can be prevented from being overwritten, and new data can be prevented from being stored. Furthermore, new data corresponding to a predetermined acoustic environment can be stored in the memory location by selectively overwriting old data in the memory location.

  The hearing prosthesis may further comprise data processing means. The data processing means receives an output from the acoustic analysis means. Based on this output, the data processing means can calculate the intensity of the sound received by the microphone. In addition, the data processing unit can calculate the strength of sound that can be heard by a person having normal hearing ability, or the strength of sound that can be heard by a person having some kind of hearing impairment. The data processing means can also calculate other acoustic indicators and psychoacoustic indicators received by the microphone. The data processing means may use an acoustic state indicator as input data for one or more equations stored in the third data memory location. This allows the user to evaluate the optimum sound processing operation of the sound processing means in the sound environment determined by the sound analysis means.

  The data processing unit further uses the auditory prosthesis characteristic data stored in the second data memory location and the optimal acoustic processor data obtained from the equation to automatically and continuously use the acoustic processing means. Appropriate setting conditions can be determined and the user can be provided with an optimal output signal for the acoustic environment currently experienced.

  In a preferred example, the acoustic processing means includes an amplification means and a gain control means. The amplification means can be adjusted in the first mode, allowing the user to optimize the gain at each or all frequencies of the amplification means in a particular acoustic environment. After optimization, the hearing prosthesis is driven in the second mode to adjust the amplification characteristics of the amplification means to an optimum level. That is, the variable processing factor can be an amplification gain at each frequency or at all frequencies.

The gain at each frequency or all frequencies of the amplification means can be calculated using a formula of a predefined type. The formula is
Gi = ai + bi ^* max (Li, ci) + di ^* (SNRi-SNRav) (1)
Can be expressed as

here,
i = number of frequency bands
G = Gain for band i
ai = training coefficient for band i
bi = Training coefficient for band i
ci = Training coefficient for band i
di = Training coefficient for band i
Li = Sound pressure level at microphone in band i
SNRi = Signal-to-noise ratio (SNR) in band i
SNRav = Average SNR across all bands
Acoustic or psychoacoustic parameters such as higher-order moments in the signal spectrum and changes in these moments, or other statistical parameters or acoustic signals, or a combination of the statistical parameters and acoustic signals, and arbitrary coefficients The gain or processing factor can also be calculated using an expression composed of a combination of. For example, factors such as the speed at which the hearing prosthesis reacts and changes in the acoustic environment can be calculated. The selection of the formula to be used can be determined depending on the usage environment without departing from the scope of the present invention.

In the above specific example, the training coefficient includes a, b, c, and d, and as a result, an amplification gain G that is a variable processing factor is derived.
Thus, one or more processing factors of the acoustic processing means can be adjusted by a user using the control means or multiple control means. Similarly, the user can adjust one or more parameters of the acoustic processing means by using the control means or the multiple control means.
(i) Output signal volume
(ii) The gain of the output signal at a particular frequency relative to other frequencies, such as the midrange frequency gain, can be amplified or attenuated compared to the high or low range frequency gain.
(iii) Slope control that adjusts the low range and high range frequency gains in opposite directions while the mid range frequency gain does not change. It is possible to select an optimum setting state for a variable processing factor for the acoustic environment. In the multiplex operation of the acoustic processing means, the user can select an optimum state for one or more variable processing factors of the acoustic environment experienced by the user by driving the indicator means. Therefore, as well as one or more variable processing factors, one or more operations of the acoustic processing means can be adjusted in conjunction with the selection. Each time the indicator means is driven, the gain in each frequency band can be recorded along with a data set indicative of the acoustic environment received by the microphone.
The data set is used with the previous data set by the data processing means to calculate the gain equation coefficient that best matches the recorded training data in each band. The recording gain in each frequency band can be used to calculate the gain equation coefficient.

  When driving in the first mode, the data processing means does not calculate an optimum coefficient of the above-described equation relating to gain until a predetermined number of selections are performed by the user. For example, the optimal coefficient may not be calculated until at least 50 selections are performed by the user. If the number of selections is not predetermined, the acoustic processing means automatically outputs an output adapted to the current environment based on a predefined factor and / or a variable processing factor in the second mode. To calculate. When a predetermined number of selections are made, the sound processing means calculates a coefficient of an expression related to an optimal gain based on the user's previous preference in the first mode, and the second mode The variable processing factor can be calculated automatically and continuously using the equation. In the acoustic processing means, the optimum coefficient of the formula relating to the gain can be calculated before the user selects a preset number of times. However, using the equation and the calculated coefficient, do not use the calculated coefficient in the second mode until a variable processing factor that the user deems preferable with some accuracy is predicted. Is preferred.

  Expressions can also be avoided in determining the optimal variable processing factor for different environments. The optimally adjusted variable processing factor may be stored at a location in the fourth data memory determined by acoustic environment data provided by the acoustic analysis means. Prior to execution of the first mode, the fourth data memory location is loaded with processing factors for corresponding acoustic environment parameter values obtained using empirical observation or conventional techniques. During operation of the first mode, the optimally adjusted processing factor is stored in a location of the fourth data memory location determined by acoustic environment data supplied by the acoustic analysis means. The optimally adjusted processing data can be overwritten on pre-existing old data or combined with pre-existing old data at the same location by using mathematical and / or statistical techniques You can also. During operation in the second mode, the acoustic environment parameters and neuroacoustic parameters supplied by the acoustic analysis means can be used to indicate the fourth data memory location and are stored in the indicating location. The value is used to determine the processing factor value of the acoustic processing means. The processing factor applied to the acoustic processing means is gradually converged to the target value to prevent an undesirable acoustic effect from being caused by the factor changing rapidly or instantaneously. To do. Note that the expressions stored in the fifth data memory location and the third data memory may not be required. Therefore, the change of the processing factor to the acoustic environment is not limited to the relationship predefined in the above equation.

  The optimally adjusted variable processing factor can be stored in the fourth data memory location, and mathematical and / or statistical techniques can be used in calculating the optimal value of the factor. In this example, the expression stored in the third data memory location is not required. Also, there is no need to store acoustic environment data directly in the fifth data memory location or to store acoustic environment data for indicating setting data in the fourth data memory location. In this example, before the hearing aid or cochlear implant output becomes unpleasant and uncomfortable, the processing factor does not change with respect to the acoustic environment such as the maximum allowable level of the output, so the processing factor is simplified. Can do.

  The user can adjust the artificial auditory organ to provide an optimal variable processing factor for different listening criteria, such as maximizing speech intelligibility, listening comfort, etc. . Further, in the adjustment process, a formula similar to the formula (1) including an acoustic environment and / or a neuroacoustic parameter related to a specific listening criterion can be used. When driving in the second mode, the variable processing factor is automatically applied to the predicted weighted combination of listening criteria determined by the coefficients used in the equation and the acoustic environment and / or neuroacoustic parameter values. Can adapt.

  Also, in the first mode, the user instructs a listening criterion to make a preferred adjustment of the variable processing factor by the indicator means. Also, the hearing prosthesis automatically predicts the listening criteria from the acoustic environment and / or neuroacoustic parameter values associated with different listening criteria and / or signals such as received speech and music. Can do.

  The fourth data memory location (referred to as the first data memory location in claim 76) is divided into sections for different listening criteria, and the optimally adjusted variable processing factor is: Under the user's adjustment, it can be stored in a memory location determined by the listening criteria.

  A data memory location of the fifth data (referred to as an additional data memory location in claim 77) is an acoustic environment or neuroacoustic parameter corresponding to a value stored in the fourth data memory location Can be divided into sections according to different listening criteria for storage. In such a configuration, the data in each section of the fourth and fifth data memory locations calculate the optimum coefficient of the similar variable processing factor equation of equation (1) for each listening criterion. It is preferable to use for this purpose. In the second mode, the user can indicate the current listening criteria via the indicator means. Also, in the operation in the second mode, the listening criterion or the weighted criterion is predicted from the presence of acoustic parameters and / or neuroacoustic parameters associated with different listening criteria, or signals such as speech and music. Can do. Further, the listening criteria or the weighted combined criteria can be predicted from one or more training listening criteria equations having acoustic environment and / or neuroacoustic parameters. In this case, the optimal coefficient for each training listening criterion is calculated from the data stored in the corresponding sections of the fourth and fifth data memory locations. When the listening criteria or weighted combined listening criteria are automatically instructed by the user or the auditory prosthesis, the optimal variable processing factor is an expression of a form similar to (1) for each criterion. And can be combined with each other according to the listening criteria.

  In the first mode, the optimally adjusted variable processing factor is stored in a listening criterion instructed by the user via the indicator means or a listening criterion predicted by the auditory prosthesis. It can be used with the acoustic environment and / or neuroacoustic parameters indicating the fourth data memory location. In the second mode, the acoustic environment and / or neuroacoustic parameters, and the indicated or predicted listening criteria indicate the fourth data memory location, and the optimal variable processing factor for the current condition. Can be used to get. Note that the listening criteria or weighted combined listening criteria may not be used to indicate the fourth data memory location. Further, in the first mode, the processing factor stored in each location of the fourth data memory location may be changed according to a weighted combination of listening criteria for the particular acoustic environment.

  In the above example, the listening criteria or weighted combined listening criteria may be indicated by the user by using indicator means such as a switch, toggle switch or push button group provided on the housing of the hearing prosthesis. Can be. The indicator means can also be provided on an isolated unit.

The present invention also provides:
A microphone that receives sound and generates a microphone signal corresponding to the received sound;
An output device that provides an acoustic signal in a form receivable by a user;
Acoustic processing means for receiving and processing the microphone signal and generating an output signal in a form suitable for operation of the output device;
Data analysis means for receiving the microphone signal and outputting a data set representative of the acoustic environment;
Data memory means for storing a plurality of setting states;
Analyzing the stored setting state, and comprising data processing means operated to output a control signal to the acoustic processing means,
The acoustic processing means is operable in a first mode, in which the output signal of the acoustic processing means can be adjusted according to a user preference for current acoustic environmental characteristics. Including at least one variable processing factor that can be adjusted by the user,
Based on receipt of the control signal, the acoustic processing means is operable in a second mode, and the at least one variable processing factor is automatically based on a variable processing factor previously adjusted by the user. Adjusted,
The data memory means relates to an auditory prosthesis (second auditory prosthesis) that stores the setting state in the first mode.

The second auditory prosthesis has the same components as those of the first auditory prosthesis, and these components have the same functions and effects as each other.
The second hearing prosthesis has data memory means for storing the optimum setting state determined by the user for different acoustic environments. This recording uses data processing means to calculate the coefficients of one or more equations used to predict the optimal state of the processing operation in the speech processor when the user is exposed to different acoustic environments. Used for.

  The hearing prosthesis can be adjusted to output an audio signal to one ear of the user. Moreover, it can adjust so that an audio | voice signal may be output with respect to both the said user's ears. Also, the input signals to the two hearing prostheses can be coupled to the acoustic analysis means via wires or wirelessly. In the example described above, the control means can be located on the housing of each hearing prosthesis. Further, the control means can be provided on an isolation unit provided for each auditory prosthesis, or can be provided on each unit common to the auditory prosthesis.

The hearing prosthesis can be a hearing aid. In this case, the output device is an earphone that receives and amplifies the output signal from the acoustic processing means and transmits it to the user's ear.
The hearing prosthesis may be an implant hearing aid. In this case, the output device can be a vibration mechanism mechanically coupled to the middle ear or the inner ear.

  Furthermore, the hearing prosthesis can be a cochlear implant. In this case, the output device may comprise a receiver / stimulator unit that receives the encoded stimulus from the acoustic processing means and outputs a stimulus signal to be transmitted to the cochlear implant via an electrode array. it can. The sound processing means may comprise a speech processor, which uses a coding strategy to receive the sound received by the microphone before or after processing the microphone signal corresponding to the variable processing factor. The speech can be extracted from. Furthermore, the speech processor may perform a speech spectrum analysis of the acoustic signal and output channel amplitude level. The conversion from the spectrum of the acoustic signal to the electrical output channel amplitude level can be determined by a variable processing factor based on the previously selected variable processing factor. The channel amplitude level may include a threshold level and a discomfort level that are processing factors based on previous adjustments and selections by the user. In addition, the acoustic processor can classify the output by their size and alerts the “spectral maxima” as used in the SPEAK strategy developed by “Cochlear LTD”. Can be.

  The receiver / stimulator unit is preferably placed in a housing that is implantable for the user. The housing for the receiver / stimulator unit is implanted in a recessed portion of the bone behind the ear, preferably located behind the mastoid process.

  The speech processing means is preferably attached to the user's body so that in use, signals are transmitted through the user's skin. The signal propagates from the processing means to the receiving means and from the receiving means to the processing means. The receiver / stimulator unit may include a receiver coil that is tuned to receive an RF signal from a transmitter coil attached to the exterior of the user. The RF signal may include an FM signal. The receiver coil preferably transmits a signal to a transmitter coil that is to receive the signal.

  It is preferable that the transmitter coil is attached in the vicinity of the implant position of the receiver coil via a magnet that exerts a relatively attractive force attached at the center position or at a different position.

  In use, the microphone is preferably attached to the user's ear wing, but can also be attached to other suitable locations, such as the user's clothing. The speech processor preferably encodes the sound received by the microphone into a continuous electrical stimulation algorithm. The encoded electrical signal is transmitted to the receiver / stimulator unit using a transmitter coil and receiver coil of the receiver / stimulator unit. The receiver / stimulator unit can demodulate the FM signal and distribute the electrical pulses to the appropriate electrode portions by an algorithm consistent with the selected speech coding strategy.

The external element housing the processing means preferably also houses a power source. The power source can comprise one or more rechargeable batteries. The receiver / stimulator coil supplies a predetermined power to the receiver / stimulator unit and the electrode array in accordance with percutaneous guidance.
In the example described above, including external elements, the microphone, the speech processor, the power source, etc. can be implanted. In this example, the implanted component is contained within a sealed housing or contained within a housing used for the stimulator unit.

Furthermore, the present invention provides
A method for adjusting a hearing prosthesis by a user in an acoustic environment,
Receiving sound from a microphone and generating a microphone signal corresponding to the sound;
Providing an acoustic signal in a form receivable by the user via an output device;
Performing a processing operation based on the microphone signal via an acoustic processing means to generate an output signal in a form suitable for the operation of the output device;
Comprising setting a setting state in the data memory means,
The acoustic processing means is operable in a first mode, in which the output signal of the acoustic processing means can be adjusted according to a user preference for current acoustic environmental characteristics. Including at least one variable processing factor that can be adjusted by the user,
The acoustic processing means is operable in a second mode, and the at least one variable processing factor is automatically adjusted based on a variable processing factor previously adjusted by the user;
The data memory means relates to a method for adjusting a hearing prosthesis, characterized in that the setting state in the first mode is stored.

The present invention also provides:
A method for adjusting a hearing prosthesis by a user in an acoustic environment,
Receiving sound from a microphone and generating a microphone signal corresponding to the sound;
Providing an acoustic signal in a form receivable by the user via an output device;
Performing a processing operation based on the microphone signal via an acoustic processing means to generate an output signal in a form suitable for the operation of the output device;
Receiving the microphone signal in a data analysis means and outputting a data set representative of the acoustic environment;
Storing a plurality of setting states in the data memory means;
Analyzing the stored setting state, and outputting a control signal to the acoustic processing means,
The acoustic processing means is operable in a first mode, in which the output signal of the acoustic processing means can be adjusted according to a user preference for current acoustic environmental characteristics. Including at least one variable processing factor that can be adjusted by the user,
Based on receipt of the control signal, the acoustic processing means is operable in a second mode, and the at least one variable processing factor is automatically based on a variable processing factor previously adjusted by the user. Adjusted,
The data memory means relates to a method for adjusting an artificial hearing organ, characterized in that the setting state in the first mode is stored.

According to the present invention, the user can easily adjust the processing means in normal use of the hearing prosthesis. In addition, according to the present invention, the user can adjust the hearing prosthesis and automatically adjust its operation. This has many advantages as shown below.
(1) Since the user can control both the hearing aid and the cochlear implant in the best condition, the user's satisfaction with the device is improved.
(2) Each user can optimize processing parameters according to their preferences and needs, thus improving listening comfort and / or speech clarity and / or substantial sound quality can do.
(3) When a device with different or additional parameters is required in the future, a training algorithm that effectively cooperates with the device can be generated.
(4) Since the training (adjustment) for the hearing prosthesis can be performed in daily life of the user, the hearing prosthesis can be adjusted without paying expensive medical expenses, and It can be executed in a state that matches the conditions of life. As a result, the adjustment can be performed in conformity with the actual use rather than in conformity with the ideal state by medical treatment.
(5) Generate a training algorithm that works effectively in the environment by automatically using the correlation between the preferred processing factor and the acoustic characteristics established based on the training without any training by the user can do.

  The present invention is not limited to an artificial ear, but can be used for a known type of artificial ear as shown in FIG.

  The artificial ear is composed of two main components, one is an external element that includes a speech processor 29 and the other is an internal element that includes an implant receiver and a stimulator unit 22. The external element includes a microphone 27. The speech processor 29 is attached behind the outer ear 11 in this figure. The artificial ear may have other configurations. A transmitter coil 24 is attached to the speech processor 29 and is configured to transmit a predetermined electrical signal to the implant unit 22 via an RF link.

  The implant element includes a receiver coil 23 for receiving power and data from the transmitter coil 24. A cable 12 is provided that extends from the implant receiver and stimulator unit 22 to the cochlea 12 and terminates in an electrode array 20. Accordingly, the received signal is supplied by the array 20 to the nerve cells in the basement membrane 8 and the cochlea 12 so that the auditory nerve 9 can be stimulated. The driving principle of such a device is described, for example, in USP 4,532,930.

As shown diagrammatically in FIG. 1, the artificial ear electrode array 20 is traditionally inserted at the first position of the tympanic floor within the total number of turns of the cochlea.
A block diagram of an example of a hearing prosthesis of the present invention is shown as 30 in FIG. This block diagram shows the characteristics of both an artificial ear and a hearing aid. The diagram is merely an example, and the present invention need not have the characteristics of both an artificial ear and a hearing aid.

  The hearing prosthesis 30 includes a microphone 27. The microphone 27 receives sound and generates a microphone signal corresponding to the received sound. The hearing prosthesis 30 also includes an output device that generates an acoustic signal in a form that can be received by a user of the device. As is apparent from the figure, the output device can include an earphone 31 when the hearing prosthesis 30 is a hearing aid. If the hearing prosthesis 30 is an artificial ear, the output device comprises an encoder / transmitter unit 32 which outputs the encoded data signal to the external transmitter coil 24.

  The hearing prosthesis 30 further includes an acoustic processing unit 33 that is operable to receive a microphone signal provided by the microphone 27 and is suitable for operation of the earphone 31 or the encoder / transmitter unit 32. The output signal can be generated in various forms.

  The characteristics and function of the acoustic processor 33 depend on whether the hearing prosthesis 30 is an artificial ear or a hearing aid. In the case of a hearing aid, the acoustic processor 33 includes at least an amplifier, and in the case of an artificial ear, the acoustic processor 33 includes a speech processor that uses a coding strategy for extracting speech behavior from the amplifier and the sound received by the microphone 27. In the illustrated example, the artificial ear speech processor can perform an acoustic spectrum analysis of the acoustic signal and output a channel amplitude level. The acoustic processor can classify the outputs by their size and can alert against a “spectral maxima” as used in the SPEAK strategy developed by “Cochlear LTD”. However, other coding strategies can be employed.

  In the present invention, the acoustic processor 33 comprises at least one variable processing factor such as an amplification factor. The variable processing factor is adjusted in the first mode of operation, and the output signal of the acoustic processor 33 is optimized to match user preferences in at least one acoustic environment. For example, the amplification characteristics of the amplifier can be controlled by the user of the hearing prosthesis and can be adapted to ambient background noise in a particular environment.

  The hearing prosthesis 30 further stores at least data indicating the setting state selected by the user, and stores a data set indicating the characteristics of the acoustic environment when the state is set and the state is selected. Data memory means 34 are provided.

The acoustic processor 33 recalculates a trainable coefficient after adjustment by the user in the first mode.
The acoustic processor 33 may be able to provide two or more optimal setting states for user selection. One of these setting states is automatically calculated by the processor, and the other setting states are systematically different from the setting states.

  In this case, the user compares the operation state of the hearing prosthesis during operation in a specific acoustic environment when operated in each setting state, and the user is most likely to perform the operation from the setting state to the specific acoustic environment. It is preferable to select a suitable setting state. The setting state selected by the user is stored in the data memory means 34 together with data representing the specific acoustic environment as appropriate. This process is repeated and the data processing unit 38 collects user preferences and monitors whether the user preferences for a particular setting state change in time or use. Thus, the user can select or determine an optimal setting state as appropriate.

  In this example, the user can change the setting state by operating the control means 36 consisting of a toggle switch or a button pair, and the setting state by operating the indicator means indicated by the switch 35 in FIG. Can be selected. The switch 35 and the control means 36 can be attached to the housing of the hearing prosthesis, or although not shown, can be provided on a unit that is spaced apart.

  The processing operation of the acoustic processor 33 can be performed in different ways depending on the user. In this case, rather than allowing the user to select an optimal setting state, the user can adjust the control means 36 to change the processing operation of the sound processor unit 33. When the user adjusts the control means 36 to select the optimum setting state for the specific acoustic environment that the user thinks, the user operates the switch 35 to select the setting state and the specific sound appropriately. Data representing the environment is stored in the data memory means 34. When the switch 35 is driven, it is handled by the acoustic processor unit 33 as if the particular setting state at the predetermined time was determined by the user to be optimal in the particular acoustic environment.

  Control means 36 includes a rotary wheel control mounted on the housing of the hearing prosthesis 30. A switch 35 can also be mounted on the housing of the hearing prosthesis 30. Although not shown, the switch and the controller can be mounted on a unit that is spaced apart.

  The setting state selected by the user as being optimal for a plurality of acoustic environments is appropriately stored in the data memory means 34 together with data representing the acoustic environment. The acoustic processor 33 is continuously operated in the second mode, and can be operated for a predetermined time in the first mode. In the first mode, the sound processor 33 can be operated each time the user adjusts the control means 36 and selects an item considered to be optimal for a specific acoustic environment. I can leave. The training time can be set as long as the user desires, and when the training is completed, the hearing prosthesis 30 can send a signal to the user. In this case, the hearing prosthesis 30 can indicate that the training time has ended. The end of the training time ends when it becomes impossible to select a setting state different from the setting state already evaluated by the hearing prosthesis 30.

  The hearing prosthesis 30 can further include an acoustic analysis module 37. The acoustic analysis module 37 receives an input signal from the microphone 27 and monitors the acoustic environment of the user. The acoustic analysis module provides an output representative of the monitored acoustic environment.

  In the illustrated example, the data memory means 34 comprises five data memory locations. In this example, the first data memory location 34 a includes user hearing data and / or individual data for one or more sounds used by the hearing prosthesis 30. The second data memory location 34 b contains the characteristic data of the hearing prosthesis 30. The third data memory location 34c comprises one or more formulas used by individual users to predict the optimal processing operation of the acoustic processor unit 33 in different acoustic environments. The fourth data memory location 34d stores the optimal acoustic processing data selected by the user. The acoustic environment corresponding to the optimal acoustic processing data stored in the fourth data memory means can be appropriately stored in the fifth data memory location 35e.

  In the illustrated example, the fourth data memory location 34d stores 400 optimal acoustic processing data, which is a predefined maximum number of data. However, the maximum value may be another value. In the illustrated example, a data processing unit 38 is used. The unit 38 will be described in detail below. The unit 38 does not use all the accumulated data, but also uses a predetermined number of the most recently recorded data. In this case, the data processing unit 38 uses only the latest 256 pieces of data when calculating the optimum formula coefficient. When the memory location is full, new data is stored in the memory location by overwriting the old data in the memory location. Therefore, the newest data can always be stored in the hearing prosthesis. In another aspect, old data can be prevented from being overwritten so that new data is not stored after the memory location is full. In another aspect, a rule for overwriting the old data can be provided based on the value of the old data.

  As described above, the hearing prosthesis can further comprise a data processing unit 38. The data processing unit 38 receives the output from the acoustic analysis module 37. Based on this output, the data processing unit 38 can calculate the intensity of the sound received by the microphone 27. In the illustrated example, the data processing unit 38 can calculate the intensity of sound that a person with normal hearing can hear, or the intensity of sound that a person with some hearing impairment can hear. The data processing unit 38 can also calculate other acoustic and psychoacoustic indicators received by the microphone 27. The data processing unit 38 can use the acoustic state indicator as input data for one or more equations stored in the third data memory location 34c. This allows the user to evaluate the optimal acoustic processing operation of the acoustic processor 33 in the acoustic environment determined by the acoustic analysis module 37.

  The data processing unit 38 further uses the auditory prosthesis characteristic data stored in the second data memory location 34b and the optimal acoustic processor data obtained from the above equation to automatically and continuously The user can be provided with an optimal output signal for the acoustic environment currently experienced.

  As described above, the acoustic processor 33 includes amplification means and gain control means 36. The data processing unit 38 is driven in the second mode and calculates the operating state of the acoustic processor 33 so that it can provide optimal amplification characteristics in any environment, as represented by the output of the acoustic analysis unit 37. .

  The hearing prosthesis can also be operated in the first mode. In this case, the operating state of the amplifier can be adjusted by the user through the control means 36 so that the amplification characteristics in the current acoustic environment are optimized.

If the hearing prosthesis is used in any environment, including environments that the user has never experienced before, the gain of the amplifier can be calculated by using a predefined form of the equation. In this example, the equation is
Gi = ai + bi ^* max (Li, ci) + di ^* (SNRi-SNRav) (1)
Can be expressed as
here,
i = number of bands
G = Gain for band i
ai = training coefficient for band i
bi = Training coefficient for band i
ci = Training coefficient for band i
di = Training coefficient for band i
Li = Sound pressure level at microphone in band i
SNRi = Signal-to-noise ratio (SNR) in band i
SNRav = Average SNR across all bands
For each band i, training data as shown below is stored;
Acoustic pressure level, ie SPL, Li (dB SPL),
Signal-to-noise ratio in band i-average signal-to-noise ratio in all bands,
That is, SNRi-SNRav (in dB),
Preferred gain (in dB).

  The above-described values can be calculated based on signals received by the microphone 27 within a predetermined time before actual operation. The value can be calculated based on signals received by the microphone 27 within a predetermined time before the operation and within a predetermined time after the operation. The stored Li is the average value of the SPL at the predetermined time, RMS, and the stored Gi is before the button is pressed, and after the user presses the button, the predetermined gain before the preferred gain adjustment is performed. Average value of gain. The SNR in the band i is currently calculated by subtracting the SPL of the portion exceeding 90% from the SPL of the portion exceeding 10% of the time in the band i within the predetermined time. It can be derived more accurately by evaluating the modulation depth of the signal. A more accurate SNR evaluation technique or speech / noise ratio evaluation technique can also be used.

  The stored training data can be used, for example, up to 256, and a number of similar equations related to equation (1) can be formed. The resulting series of equations can be in linear form, but the coefficients bi and ci can be multiplied together, in which case the series of equations is not linear, so the series of equations is initially linear. Keep it. ci is set to a predetermined value in advance, and max (Li, ci) can be executed based on the ci value and the stored Li value. When the Li value is large, the calculation result in the parentheses is Li. The optimal ai, bi and ci are then calculated based on direct numerical methods. In this case, the coefficient may be obtained by applying the least square method to Gi obtained based on the stored Gi and the corresponding Li value and the stored SNRi-SNRav. This operation is performed for at least four different values of ci, for example, 35, 45, 55 and 65 dB SPL. Thus, the coefficient obtained by the least square method is selected as an optimum one and is used for signal processing. However, the value of bi is not outside the range of −1.0 to +1.0, or is limited to the case where the number of operations is 50 or less. The training coefficient can also be determined by other methods.

  The direct numerical method is lower-upper (LU) decomposition and back substitution. The numerical method is various Gaussian elimination methods in which a series of expressions are stored in a memory in a matrix form of Ax = b. Matrix A is the stored acoustic environment data and x is a vector containing the coefficients to be calculated (ie ai, bi and ci). The LU decomposition method is operated on the matrix and solves for the vector x. Other Gaussian elimination methods or direct numerical methods can also be used.

For example, the following formula regarding the training coefficient can be obtained by performing the above-described operation four times.
25 = ai + (bi ^* 35) + (di ^* 0)
20 = ai + (bi ^* 45) + (di ^* 0)
15 = ai + (bi ^* 55) + (di ^* 0)
10 = ai + (bi ^* 65) + (di ^* 0)
In this case, ai = 42.5, bi = -0.5, ci = 35 and di = 0.0.
If such a coefficient is used, an error is given to a value of 0 dB. In actual situations, people's preference for amplification may vary, and training data may vary. Therefore, the Gi value located on the left side of the equal sign in the above formula is not constant, and as a result, the training coefficient value may be different.

  Acoustic or psychoacoustic parameters such as higher-order moments in the signal spectrum and changes in these moments, or other statistical parameters or acoustic signals, or a combination of the statistical parameters and acoustic signals, and arbitrary coefficients The gain or processing factor can also be calculated from an expression composed of a combination of. For example, factors such as the speed at which the hearing prosthesis reacts and changes in the acoustic environment can be calculated. The selection of the formula to be used can be determined depending on the usage environment without departing from the scope of the present invention.

In the above specific example, the training coefficient includes a, b, c, and d, and as a result, an amplification gain G that is a variable processing factor is derived.
One or more processing factors of the acoustic processor 33 can be automatically derived using an equation similar to equation (1) and can be adjusted by the user using the control means 36 or multiple control means. . In this example, the control means 36 allows the user to control one or more parameters of the acoustic processor 33.
(i) Output signal volume
(ii) The gain of the output signal at a particular frequency relative to other frequencies, such as the midrange frequency gain, can be amplified or attenuated compared to the high or low range frequency gain.
(iii) Slope control for adjusting the low range and high range frequency gains in opposite directions while the mid range frequency gain does not change. Decide what it is. By pressing the switch 35, the gain in each frequency band is recorded together with the data representative of the acoustic environment received by the microphone 27. These data are processed using the data processing unit 38 together with the previous data, and the coefficient that can most predict the user's preference can be calculated from the training data recorded in each band from the above formula. The data processing unit 38 accesses the preferred amplification characteristics and the preferred acoustic environment for these characteristics and calculates a general relationship between the amplification characteristics and the acoustic environment. Thus, the automatically calculated amplification characteristics can change in a complex and defined manner as the acoustic environment changes. For example, in this example, the gain at each frequency varies according to the SNR at each frequency relative to the overall input level and the SNR at other frequencies.

  The illustrated data processing unit 38 does not calculate the optimum coefficients of the above-described equation for gain until a predetermined number of selections are performed by the user. In the illustrated example, the hearing prosthesis 30 does not calculate the optimal coefficient until at least 50 selections are performed by the user. If the number of selections is not predetermined, the acoustic processor 33 preferably outputs a signal obtained based on an initially predetermined training factor. The initially predetermined training factor for each user can be calculated using conventional methods in prescribed auditory prostheses or can be determined by performing empirical trial and error operations. it can. When the preset number of times is selected, the data processing unit 38 immediately recalculates the training coefficient every time the user operates the switch 35 and the control means 36 posts the optimum state. In another example, the data processing unit 38 may recalculate the training coefficient before making a user-preset number of selections. However, the training coefficient obtained in this way is selected from the above formula until the user's preference can be accurately predicted and / or within the preferable minimum range of the acoustic environment. It doesn't really apply until you do it.

  As another example, the data processing unit 38 can determine the optimal variable processing factor for different environments without using the equations stored in the data memory location 34c. The optimally adjusted variable processing factor is stored in a location determined by the corresponding acoustic environment data supplied by the acoustic analysis means 37 in the fourth data memory location 34d. Prior to the execution of the first mode, the fourth data memory location 34d is loaded with processing factors for the corresponding acoustic environment parameter values obtained using empirical observation or conventional techniques. During operation of the first mode, the optimally adjusted processing factor is stored in a location determined by the acoustic environment data supplied by the acoustic analysis means 37 in a fourth data memory location 34d. For example, the fourth data memory location 34d stores a multi-dimensional (ie, N-dimensional) lookup table or matrix. Each dimension is a different acoustic environment or neuroacoustic parameter, and these parameter values determine a location in memory location 34d where a table, matrix or preferred processing factor is stored. Therefore, the matrix is represented by N acoustic environment parameters (or neuroacoustic parameters such as speech). The optimally adjusted processing data can be overwritten on the pre-existing old data in the fourth data memory 34d, or pre-existing at the same location by using mathematical and / or statistical techniques. It can also be combined with old data. During operation in the second mode, the acoustic environment parameters and neuroacoustic parameters supplied by the acoustic analysis means 37 are used to indicate the location of the table, the matrix, or the fourth data memory location 34d. The value stored at the indicated location is used to determine the value of the processing factor for the second processing means 33. The processing factor applied to the acoustic processing means 33 is gradually converged to the target value to prevent an undesirable acoustic effect from being caused by the factor changing rapidly or instantaneously. To do. The operation of adjusting the desired value of the processing factor at a memory location that includes a pre-determined processing factor may represent the user's adjustment preference for an environment close to the current environment at the memory location 34d. . In this example, the expressions stored in the fifth data memory location 34e and the third data memory 34c are not required. Also, the change in processing factor to the acoustic parameters supplied by the acoustic analysis means 37 or to the neuroacoustic parameters calculated by the data processing unit 38 is predefined in the formula stored in the third data memory location 34c. It is not limited by the relationship.

The hearing prosthesis may be configured to output an acoustic signal to one ear of the user and may output the acoustic signal to both ears.
The hearing prosthesis can also receive a microphone signal from a microphone attached to one side of the head and output the signal to one or both ears.
FIG. 3 is a flowchart showing the logic for operating the data processing unit 38.

  The hearing prosthesis 30 is turned on and power is supplied to the components of the organ 30, including the acoustic processor 33 and the data processing unit 38, thereby starting the operation of the unit 38. Then, the operation of the unit 38 ends when the user turns off the hearing prosthesis 30 or the battery of the power source is exhausted. Although not particularly illustrated, other end modes can be set. For example, when the user's selection count reaches a predetermined number, or when the user finishes training the auditory prosthesis 30 after a predetermined period of time, or the user adjusts the control means 36, the auditory artificial The end of the operation of the unit 38 can be set when the training for the organ 30 is sufficiently performed. Further, when the user is satisfied with the performance of the hearing prosthesis 30 in a range of different acoustic environments, the audiologist or the third engine can end the handling of the hearing prosthesis 30. However, if the user can handle the auditory prosthesis arbitrarily and the user encounters a new environment, or the user's degree of audible insufficiency over time, or the user's adaptability to the auditory prosthesis changes There is no need to train again on the handling of hearing prostheses.

  FIG. 4 is a graph showing the results of initial experiments performed on the prototype of the hearing prosthesis of the present invention. The purpose of this experiment is to handle the hearing prosthesis to generate a gain greater than that provided by the hearing prosthesis prior to training in all frequency bands for any input sound. FIG. 4 shows a control output 36 (RMS control adjustment (dB unit)) adjusted to reduce the desired output as the training ability for the hearing prosthesis increases in the next group after the group including 15 selections. Indicates that this has occurred.

FIG. 5 illustrates a matrix using the acoustic parameters of equation (1).
FIG. 5 shows a state where the processing factor is stored in the two-dimensional memory space. The matrix is shown by two acoustic parameters: the acoustic pressure level for band i and the value of SNR for band i for all bands. In the present invention, it is naturally possible to use a two-dimensional or higher matrix. The numerical value at the memory location indicates the gain value. The gain value is a variable processing factor. Other than the characters shown in bold italics, the values stored in advance are shown, and the italic characters are newly set and stored based on user training.

  While the present invention has been described based on the specific examples described above, various changes and modifications can be made without departing from the scope of the present invention. The specific examples described above are merely examples, and do not limit the present invention.

It is a figure which shows the conventional cochlear implant system. 2 is a block diagram of an example of a hearing prosthesis of the present invention. 3 is a flowchart of a specific operation mode of the hearing prosthesis shown in FIG. 6 is a graph showing results of experiments performed on a prototype of the hearing prosthesis of the present invention. It is a figure which shows the memory | storage state of the processing factor in a two-dimensional memory space.

Claims (114)

A microphone that receives sound and generates a microphone signal corresponding to the received sound;
An output device that provides an acoustic signal in a form receivable by a user;
Acoustic processing means for receiving and processing the microphone signal and generating an output signal in a form suitable for operation of the output device;
Data memory means for storing the setting state;
The acoustic processing means is operable in a first mode, in which the output signal of the acoustic processing means can be adjusted according to a user preference for current acoustic environmental characteristics. Including at least one variable processing factor that can be adjusted by the user,
The acoustic processing means is operable in a second mode, and the at least one variable processing factor is automatically adjusted based on a variable processing factor previously adjusted by the user;
The hearing aid prosthesis, wherein the data memory means stores the setting state in the first mode.   The sound processing means provides two or more optimal setting states of the at least one variable processing factor selected by the user when operating in the first mode. The hearing prosthesis according to 1.   Whether the selection operation by the user is performed a plurality of times, and whether the user's preference for the predetermined setting state defined by the at least one variable processing factor is changed according to time or usage history. The hearing prosthesis according to claim 2, characterized in that it is monitored whether or not.   The number of user selections for each setting state is monitored by the acoustic processing means so that the auditory prosthesis can select an optimal setting state defined by the at least one variable processing factor. The hearing prosthesis according to claim 3.   5. The hearing prosthesis according to claim 4, wherein the user operates a control means, changes the at least one variable processing factor, and changes a processing operation of the acoustic processing means.   A user who adjusts the control means and sets a state considered to be optimal for the current acoustic environment operates the indicator means to store the setting state in the data memory means. The hearing prosthesis of claim 5.   By operating the indicator means, the sound processing means is instructed so that the setting state of the control means selected by the user is the optimum setting state for the current acoustic environment. The hearing prosthesis according to claim 6, characterized in that:   8. The hearing prosthesis according to claim 7, wherein the selected setting state is stored in the memory means based on an operation of the indicator means.   9. The hearing prosthesis according to claim 1, wherein the data memory means stores a data set representative of at least one acoustic environment characteristic.   10. The data set representative of claim 9, wherein the data set representative of the at least one acoustic environmental characteristic is stored in the data memory means by driving the indicator means by the user. Hearing prosthesis.   11. The hearing prosthesis of claim 10, wherein the at least one variable processing factor is automatically adjusted based on the acoustic environment for which the factor was selected.   The sound processing means is operated in the first mode for a predetermined time when the sound processing means is operated in the second mode, according to any one of claims 7 to 11. Hearing prosthesis.   When the acoustic processing means is operated in the second mode, the acoustic processing means adjusts the control means in the first mode so that the user adjusts the control means to be optimal for the current acoustic environment. The auditory prosthesis according to any one of claims 7 to 11, wherein the acoustic processor is operated each time an item considered to be a state is selected.   The auditory prosthesis according to claim 1, wherein the auditory prosthesis is subjected to training for a predetermined time when operated in the first mode.   15. The hearing prosthesis of claim 14, wherein the hearing prosthesis emits a signal to the user after the training time is complete.   16. The hearing according to claim 15, wherein the training time is completed when the user stops selecting a setting state substantially different from an optimal setting state already obtained by the hearing prosthesis. Prosthesis.   The hearing prosthesis according to any one of claims 1 to 16, further comprising acoustic analysis means for receiving an input signal from the microphone and monitoring the current acoustic environment.   18. A hearing prosthesis according to claim 17, wherein the acoustic environment means provides an output representative of the acoustic environment to be monitored.   19. A hearing prosthesis according to claim 18, wherein said data memory means comprises one or more data memory locations.   The data memory means has five data memory locations, the first data memory location storing the user's hearing data and / or individual data for one or more acoustic models used by the hearing prosthesis. 20. A hearing prosthesis according to claim 19, characterized in that   21. A hearing prosthesis according to claim 20, wherein a second data memory location stores characteristic data of the hearing prosthesis.   The third data memory location stores one or more expressions and predicts an optimal processing operation of the acoustic processing means for the user under different acoustic conditions, according to claim 20 or 21. The hearing prosthesis described.   23. A hearing prosthesis according to any one of claims 20-22, characterized in that a fourth data memory location stores optimal acoustic processing data selected by the user.   24. An auditory prosthesis according to claim 23, characterized in that the data stored in the fourth data memory location is indicated according to acoustic environment data provided by the acoustic environment means.   25. The fifth data memory location stores acoustic environment data corresponding to the optimal acoustic processing data stored in the fourth data memory location. The hearing prosthesis described.   24. The hearing prosthesis of claim 23, wherein the fourth data memory location stores a predefined maximum number of optimal acoustic processing data selected by the user.   27. A hearing prosthesis according to claim 26, comprising data processing means for receiving the output of the acoustic analysis means.   28. The hearing prosthesis according to claim 27, wherein the data processing means calculates the magnitude of the sound collected by the microphone based on the output from the acoustic analysis means.   29. The data processing means calculates an acoustic and / or neuroacoustic index, such as the magnitude of the sound received by the macrophone, based on the output from the acoustic analysis means. The hearing prosthesis described in 1.   30. The hearing prosthesis according to claim 29, wherein the data processing means calculates a size of the sound when the person having normal hearing and / or a person with impaired hearing hears the sound. .   The data processing means inputs the acoustic and / or the neuroacoustic index into the one or more formulas stored in the third data memory location, and in the acoustic environment represented by the acoustic analysis means. 31. A hearing prosthesis according to claim 30, characterized by predicting an optimal processing operation of the acoustic processing means for the user.   The data processing means uses a predetermined number of the most recently stored data sets in the fourth data memory location in determining the optimal value of the at least one variable processing factor. 32. A hearing prosthesis according to claim 31, characterized in that   33. The most recent data set stored in the fourth data memory location is replaced with the oldest data debt stored in the fourth data memory location. The hearing prosthesis described.   34. The hearing prosthesis of claim 33, wherein the hearing prosthesis does not store an additional data set when the fourth data memory location is completely filled.   34. A hearing prosthesis according to claim 33, characterized in that the old data set is selectively overwritten by the newest data set of the corresponding acoustic environment.   The data processing means includes hearing prosthesis characteristic data stored in the second data memory location and optimal acoustic processor data generated by one or more equations stored in the third data memory location. And automatically and continuously determining an appropriate state of the acoustic processing means to provide an optimal output signal for the user in the current acoustic environment experienced by the user. 36. The hearing prosthesis according to any one of Items 27 to 35.   The auditory prosthesis according to any one of claims 1 to 36, wherein the acoustic processing means includes an amplification means and a gain control means.   38. The auditory prosthesis according to claim 37, wherein the amplifying means is adjustable and, in the first mode, the user optimizes a gain at each frequency of the amplifying means in a specific environment. organ.   The auditory prosthesis is driven in the second mode when the gain is optimized, and the amplification characteristic of the amplification means is automatically adjusted to an optimum level. 38. A hearing prosthesis according to 38.   The data processing unit is driven in the second mode and calculates the operation of the acoustic processor means so as to provide as much as possible the optimum acoustic amplification characteristics of any environment represented by the output of the acoustic analysis means. 40. A hearing prosthesis as claimed in claim 39.   The hearing prosthesis is simultaneously driven in the first mode, and the user changes the control means to optimize the operation of the amplification means, and the user has the amplification characteristics in the current acoustic environment. 41. A hearing prosthesis according to claim 40, characterized in that it can be optimized.   44. A hearing prosthesis according to any one of claims 37 to 41, wherein the at least one variable processing factor includes the amplification gain. 43. A hearing prosthesis according to claim 37, characterized in that the gain of the amplification means at each frequency is used in an environment as calculated by the following equation:
Gi = ai + bi ^* max (Li, ci) + di ^* (SNRi-SNRav)
here,
i = number of frequency bands
G = Gain for band i
ai = training coefficient for band i
bi = Training coefficient for band i
ci = Training coefficient for band i
di = Training coefficient for band i
Li = Sound pressure level at microphone in band i
SNRi = Signal-to-noise ratio (SNR) in band i
SNRav = Average SNR in all bands.   44. The auditory prosthesis according to claim 43, wherein when driving in the first mode, the acoustic processing means calculates the training coefficients a, b, c and d after adjustment by the user. organ.   45. The hearing prosthesis according to claim 44, wherein the user operates multiple control means to adjust multiple variable processing factors. The auditory prosthesis according to claim 45, wherein the user operates one or more of the following operations of the acoustic processor means using the control means or the multiple control means.
(i) the volume of the output signal;
(ii) Output signal gain of a specific frequency relative to other frequencies;
(iii) Slope control that adjusts the gain of the low range and high range frequency in the opposite direction when the midrange gain remains unchanged.   The hearing prosthesis according to claim 46, characterized in that, in operation of the acoustic processor means, the user selects an optimal state for each variable processing factor for the acoustic environment experienced by driving the indicator means. .   The auditory prosthesis according to claim 46, characterized in that, in multiple operations of the acoustic processor means, the user selects an optimal state for each variable processing factor for the acoustic environment experienced by driving the indicator means. organ.   49. A hearing prosthesis according to claim 47 or 48, characterized in that the gain in each frequency band is recorded in the operation of the indicator means.   50. A hearing prosthesis according to claim 49, characterized in that the gain recorded in each frequency band is used to calculate the coefficients of the equation described in claim 43.   51. A hearing prosthesis according to claim 50, wherein a data set representative of the acoustic environment received by the microphone is recorded.   The data set representative of the acoustic environment is used with the previous data set by the data processing means to calculate the coefficients that best match the training data stored in each frequency band, and to store the stored training data 52. The hearing prosthesis according to claim 51, characterized in that it includes a stored preferred variable processing factor and corresponding environmental data.   The data processing means does not calculate an optimal coefficient in the equation until a predetermined number of predefined selections are performed by the user when driving in the first mode. 54. The hearing prosthesis according to any one of 44 to 52.   54. A hearing prosthesis according to claim 53, characterized in that the predefined number of selections is 50 times.   If the predefined predetermined number of selections is not complete, the data processing means is suitable for the current acoustic environment based on predefined coefficients and / or variable processing factors in the second mode. 55. A hearing prosthesis according to claim 53 or 54, characterized in that the output is calculated automatically.   56. If the predetermined number of predefined selections are not complete, the data processing means outputs a signal calculated based on an initial, predefined training factor value. The hearing prosthesis described in 1.   The initially predetermined training factor is determined for each user by driving a prescribed hearing prosthesis based on conventional methods or by performing empirical trial and error operations. 57. A hearing prosthesis according to claim 56, characterized.   After the pre-determined predetermined number of selections are completed, the data processing means calculates an optimal coefficient in the formula based on the user's previous preferences in the first mode, and continuously. The auditory prosthesis according to any one of claims 53 to 55, wherein, in the second mode, the variable processing factor is calculated using the equation.   The data processing means does not wait for an operation to complete a predetermined number of selections before the coefficients in the formula are calculated, and in the second mode, a variable processing factor preferable for the user. 59. A hearing prosthesis according to claim 58, wherein the calculated coefficient is not used until is predicted from the equation and the calculated coefficient.   When driving in the first mode, any adjusted variable processing factor is stored in the one or more locations determined by corresponding acoustic environment data provided by the acoustic analysis means. The hearing prosthesis of claim 19.   The adjusted variable processing factor is stored in a multi-dimensional lookup table at the one or more locations, wherein each dimension is a different acoustic environment or neuroacoustic parameter, 61. A hearing prosthesis according to claim 60.   62. The hearing prosthesis according to claim 61, wherein the multidimensional lookup table is indexed by at least two parameters selected from acoustic environment or neuroacoustic parameters.   64. The hearing prosthesis according to claim 62, wherein the parameter value determines a location in the lookup table where the preferred processing factor is stored.   In the first mode, the acoustic processing means operates by loading each of the memory locations with a processing factor for the corresponding acoustic environmental parameter value obtained using empirical observation or conventional techniques. 64. A hearing prosthesis according to claim 63, characterized in that starts.   The optimally adjusted variable processing data is overwritten with previous data or combined with previous data in the same memory location using mathematical and / or statistical techniques. 65. A hearing prosthesis according to claim 64.   In the second mode, the acoustic environment and neural environment parameters supplied by the acoustic analysis means are used to indicate the memory location or the look-up table, and the value stored at the indexed location is the 66. Auditory prosthesis according to claim 65, characterized in that it is used to set a corresponding processing factor value for the acoustic environment means.   The processing factor applied to the acoustic processing means converges to a target value, and prevents the undesirable acoustic effect from being generated by the factor changing rapidly or instantaneously. 68. A hearing prosthesis according to claim 66, characterized.   68. Auditory according to claim 67, wherein the target value is adjustable to represent the user's adjustment preferences for an environment close to the current environment at the one or more locations. Prosthesis.   20. An auditory prosthesis according to claim 19, characterized in that an optimally adjusted variable processing factor is calculated and stored at the one or more locations by mathematical and / or statistical techniques such as a weighted average. organ.   The artificial hearing organ is tuned to provide an optimal variable processing factor for different listening criteria, such as maximizing speech intelligibility, listening comfort, etc. Item 20. The hearing prosthesis according to any one of Items 1 to 19.   71. The auditory prosthesis of claim 70, wherein in the adjusting process, an expression including an acoustic environment and / or a neuroacoustic parameter highly related to a specific listening criterion is used.   When driving in the second mode, the variable processing factor is automatically applied to the predicted weighted combination of listening criteria determined by the coefficients used in the equation and the acoustic environment and / or neuroacoustic parameter values. 72. A hearing prosthesis according to claim 71, characterized in that   2. The listening instruction according to claim 1, wherein when the sound processing means is operated in the first mode, the user instructs the listening means to make a preferable adjustment of the variable processing factor by the indicator means. The hearing prosthesis according to any one of -19.   Values of acoustic environment and / or neuroacoustic parameters associated with different listening criteria so that the hearing prosthesis makes a favorable adjustment of the variable processing factor when the acoustic processing means is operated in the first mode. The hearing prosthesis according to claim 1, wherein a listening criterion is automatically predicted.   75. The auditory prosthesis of claim 74, wherein the auditory prosthesis automatically predicts the listening criteria from the presence of signals such as received speech and music.   A first data memory is divided into sections for different listening criteria, and the optimally adjusted variable processing factor is stored in a memory location determined by the listening criteria under the adjustment of the user. 76. A hearing prosthesis according to claim 75, characterized in that   According to different listening criteria, an additional data memory location for storing an acoustic environment or a neuroacoustic parameter corresponding to a value stored in the first data memory location is divided into sections. 77. A hearing prosthesis according to claim 76.   78. Data in each section of the first and the additional data memory locations is used to calculate an optimal value of a variable processing factor for each listening criterion. Hearing prosthesis.   79. A hearing prosthesis according to any one of claims 76 to 78, wherein, in a second mode, the user indicates a current listening criterion via the indicator means.   79. The operation in the second mode, wherein the listening criteria or weighted criteria are predicted from values of acoustic parameters and / or neuroacoustic parameters associated with different listening criteria. The hearing prosthesis according to any one of the above.   79. Auditory according to any one of claims 76 to 78, wherein in the operation in the second mode, the listening criteria or weighted combined criteria are predicted from the presence of a signal such as speech or music. Prosthesis.   In operation in the second mode, the listening criterion or the weighted combined criterion is predicted from one or more training listening criterion formulas having acoustic environment and / or neuroacoustic parameters, and an optimum for each training listening criterion formula is determined. 79. A hearing prosthesis according to any one of claims 76 to 78, characterized in that the coefficients are calculated from stored data of corresponding sections of the first and the additional data memory locations.   In the first mode, a listening criterion instructed by the user via the indicator means or a listening criterion predicted by the auditory prosthesis is stored in the first mode in which the optimally adjusted variable processing factor is stored. 77. A hearing prosthesis according to claim 76, used with the acoustic environment and / or neuroacoustic parameters indicating one data memory location.   In the second mode, the acoustic environment and / or neuroacoustic parameters, as well as the indicated or predicted listening criteria, indicate the first data memory location to determine an optimal variable processing factor for the current conditions. 77. A hearing prosthesis according to claim 76, characterized in that it is used for obtaining.   77. The auditory prosthesis of claim 76, wherein in the first mode, the processing factor stored in the first data memory location changes according to a weighted combination of listening criteria for the particular acoustic environment. organ. A microphone that receives sound and generates a microphone signal corresponding to the received sound;
An output device that provides an acoustic signal in a form receivable by a user;
Acoustic processing means for receiving and processing the microphone signal and generating an output signal in a form suitable for operation of the output device;
Data analysis means for receiving the microphone signal and outputting a data set representative of the acoustic environment;
Data memory means for storing a plurality of setting states;
Analyzing the stored setting state, and comprising data processing means operated to output a control signal to the acoustic processing means,
The acoustic processing means is operable in a first mode, in which the output signal of the acoustic processing means can be adjusted according to a user preference for current acoustic environmental characteristics. Including at least one variable processing factor that can be adjusted by the user,
Based on receipt of the control signal, the acoustic processing means is operable in a second mode, and the at least one variable processing factor is automatically based on a variable processing factor previously adjusted by the user. Adjusted,
The hearing aid prosthesis, wherein the data memory means stores the setting state in the first mode.   87. A hearing prosthesis according to claim 86, wherein the data memory means stores the data set output by the acoustic analysis means.   88. The hearing prosthesis according to claim 86 or 87, wherein the at least one variable processing factor is automatically adjusted based on an acoustic environment corresponding to the selected variable processing factor.   89. A hearing prosthesis according to any one of claims 86 to 88, wherein the data memory means stores optimal setting states determined by the user for different acoustic environments.   The coefficient in one or more equations used when the data processing means is exposed to a different acoustic environment, and uses the stored optimal setting state to predict the optimum operating conditions of the acoustic processing means. 90. A hearing prosthesis according to claim 89, characterized in that is calculated.   The auditory prosthesis according to any one of claims 86 to 90, wherein an audio signal is output to one ear of the user.   The hearing prosthesis according to any one of claims 86 to 90, characterized in that audio signals are output to both ears of the user.   When driving the acoustic processing means in the first mode, the acoustic processing means provides two or more possible setting states of the at least one variable processing factor for the user's selection. A hearing prosthesis according to any one of claims 86 to 92.   Whether the user's selection is repeated and whether the sound processing means has changed its user preference over time or over time for a particular setting state corresponding to the at least one variable processing factor 94. The hearing prosthesis according to claim 93, characterized in that it can be monitored.   The number of selections of the user for each setting state is monitored by the acoustic processing means so that the hearing prosthesis can select an optimal setting state for the at least one processing factor. 94. A hearing prosthesis according to 94.   96. A hearing prosthesis according to claim 95, wherein the user manipulates a control means to change the at least one variable processing factor to change a processing operation of the acoustic processing means.   A user who adjusts the control means and sets a state considered to be optimal for the current acoustic environment operates the indicator means to store the setting state in the data memory means. 96. The hearing prosthesis of claim 95.   By operating the indicator means, the sound processing means is instructed so that the setting state of the control means selected by the user is the optimum setting state for the current acoustic environment. 98. A hearing prosthesis according to claim 97, characterized in that   99. The hearing prosthesis according to any one of claims 86 to 98, wherein the hearing prosthesis is a hearing aid.   100. The hearing prosthesis according to claim 99, wherein the output device of the hearing aid receives and amplifies and transmits the output signal of the acoustic processing means to the user's ear.   99. The hearing prosthesis according to any one of claims 86 to 98, wherein the hearing prosthesis is an implant hearing aid.   102. The hearing prosthesis according to claim 101, characterized in that the output device of the implant hearing aid is a vibration mechanism mechanically coupled to the middle or inner ear.   99. The hearing prosthesis according to any one of claims 86 to 98, wherein the hearing prosthesis is a cochlear implant.   The cochlear implant output device comprises a receiver / stimulator unit that receives the encoded stimulus from the acoustic processing means and outputs a stimulus signal to be transmitted to the cochlear implant via an electrode array. 104. Auditory prosthesis according to claim 103, characterized.   The sound processing means comprises a speech processor, which uses a coding strategy to extract speech from the sound received by the microphone before or after processing of the microphone signal corresponding to the variable processing factor. 105. A hearing prosthesis according to claim 104, characterized by:   106. A hearing prosthesis according to claim 105, wherein the speech processor performs a speech spectrum analysis of the acoustic signal and output channel amplitude level.   107. A hearing prosthesis according to claim 106, wherein the conversion from the spectrum of the acoustic signal to the output channel amplitude level is determined by a variable processing factor based on a previously selected variable processing factor.   108. The hearing prosthesis of claim 107, wherein the channel amplitude level includes a threshold level and a discomfort level that are processing factors based on prior adjustments and selections by the user.   109. A hearing prosthesis according to claims 104-108, wherein the receiver / stimulator unit is located in a housing that is implantable to the user.   110. The hearing prosthesis of claim 109, wherein the housing for the receiver / stimulator unit is implanted in a recessed portion of the bone behind the ear located behind the mastoid process. 111. A hearing prosthesis according to any one of claims 105 to 110, wherein the speech processor encodes the sound received by the microphone into a continuous electrical stimulation algorithm.   112. The auditory prosthesis of claim 111, wherein the encoded electrical signal is transmitted to the receiver / stimulator unit using a transmitter coil and receiver coil of the receiver / stimulator unit. . A method for adjusting a hearing prosthesis by a user in an acoustic environment,
Receiving sound from a microphone and generating a microphone signal corresponding to the sound;
Providing an acoustic signal in a form receivable by the user via an output device;
Performing a processing operation based on the microphone signal via an acoustic processing means to generate an output signal in a form suitable for the operation of the output device;
Comprising setting a setting state in the data memory means,
The acoustic processing means is operable in a first mode, in which the output signal of the acoustic processing means can be adjusted according to a user preference for current acoustic environmental characteristics. Including at least one variable processing factor that can be adjusted by the user,
The acoustic processing means is operable in a second mode, and the at least one variable processing factor is automatically adjusted based on a variable processing factor previously adjusted by the user;
The method for adjusting an auditory prosthesis, wherein the data memory means stores the setting state in the first mode. A method for adjusting a hearing prosthesis by a user in an acoustic environment,
Receiving sound from a microphone and generating a microphone signal corresponding to the sound;
Providing an acoustic signal in a form receivable by the user via an output device;
Performing a processing operation based on the microphone signal via an acoustic processing means to generate an output signal in a form suitable for the operation of the output device;
Receiving the microphone signal in a data analysis means and outputting a data set representative of the acoustic environment;
Storing a plurality of setting states in the data memory means;
Analyzing the stored setting state, and outputting a control signal to the acoustic processing means,
The acoustic processing means is operable in a first mode, in which the output signal of the acoustic processing means can be adjusted according to a user preference for current acoustic environmental characteristics. Including at least one variable processing factor that can be adjusted by the user,
Based on receipt of the control signal, the acoustic processing means is operable in a second mode, and the at least one variable processing factor is automatically based on a variable processing factor previously adjusted by the user. Adjusted,
The method for adjusting an artificial auditory organ, wherein the data memory means stores the setting state in the first mode.

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