WO1997001314A1 - Appareil et procede permettant de commander des processeurs vocaux et de fournir des donnees d'entree privees par l'intermediaire desdits processeurs - Google Patents

Appareil et procede permettant de commander des processeurs vocaux et de fournir des donnees d'entree privees par l'intermediaire desdits processeurs Download PDF

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Publication number
WO1997001314A1
WO1997001314A1 PCT/AU1996/000403 AU9600403W WO9701314A1 WO 1997001314 A1 WO1997001314 A1 WO 1997001314A1 AU 9600403 W AU9600403 W AU 9600403W WO 9701314 A1 WO9701314 A1 WO 9701314A1
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WO
WIPO (PCT)
Prior art keywords
signals
command
commands
battery
person
Prior art date
Application number
PCT/AU1996/000403
Other languages
English (en)
Inventor
Peter Single
Bruce Macaulay
Christopher Newton Daly
Original Assignee
Cochlear Limited
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Cochlear Limited filed Critical Cochlear Limited
Priority to AU61826/96A priority Critical patent/AU6182696A/en
Priority to JP50404897A priority patent/JP2001508667A/ja
Priority to EP96920635A priority patent/EP0840581A1/fr
Publication of WO1997001314A1 publication Critical patent/WO1997001314A1/fr

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear
    • A61N1/36038—Cochlear stimulation
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • H04R25/305—Self-monitoring or self-testing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/558—Remote control, e.g. of amplification, frequency
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R29/00—Monitoring arrangements; Testing arrangements
    • H04R29/008—Visual indication of individual signal levels

Definitions

  • TECHNICAL FIELD This invention relates to apparatus for and a method of controlling the operation of devices used to enhance the aural faculties of a person, such as, for example, a cochlear implant.
  • the invention further relates to a cochlear prosthesis capable of conveying information of interest to the wearer by transmitting said data directly to the wearer in an unobtrusive and private manner. This is accomplished by incorporating the data into the processed sound stimulations which stimulate the user's auditory nerve in the normal course of operation of the cochlear implant.
  • Various devices such as cochlear implants, are being used to assist persons having a chronic aural disability or impairment which cannot be alleviated by external hearing aids. These devices typically include two sections: an external section carried on the user and an internal section which is implanted into the user.
  • the external section typically includes a microphone for converting ambient sounds into electrical signals, signal processing means for converting the electrical signals into processed signals, and a signal transmitter for transmitting the processed signals to the internal section.
  • the internal section typically includes receiver means for receiving signals from the transmitter, signal processor means for processing the received signals, and stimulating means for stimulating the inner ear of the person, such as the cochlea, in accordance with the received signals.
  • the external section further includes various manual controls for the operation of the device, such as a volume control, battery checking, and so on.
  • various manual controls for the operation of the device, such as a volume control, battery checking, and so on.
  • a problem with devices of the kind just described is that, although the microphone, transmitter and signal processing means are electronic components which are readily miniaturized, the overall size of the external section is still too large because of the manual controls which typically consist of, or are implemented, using mechanical components.
  • a further disadvantage of the existing systems is that, naturally, the person tends to hide the external section on his person, i.e. in the clothing, so that the impairment is not obvious. However, once the external section is hidden, it is difficult to manipulate its manual controls.
  • the external component of some of the devices may include status indicators, relating to various functions of the device, to the wearer.
  • This technique has several disadvantages.
  • One major disadvantage is that it is relatively conspicuous and counter to the general prosthetic device design objective of presenting as low a profile as possible.
  • Another disadvantage of this technique is that alarms may go unnoticed by the user. For example, if the alarm is provided as a visual indicator such as an LED mounted on the external component, then if the user wears this external component behind the ear, or in a pocket, the warning indication will not be detected unless a deliberate effort is made to inspect the indicator. Furthermore, the diligent user will regularly check such status indicators only to find that all is well and that there has been no need to have taken the trouble of checking.
  • a further disadvantage of the present technique is that it lacks flexibility since it is arranged and constructed to monitor and indicate only very specific functions. It is possible to make use of an audible alarm, for example by means of a small loudspeaker or tone-generator, rather than a visual one, however, this approach also presents problems.
  • a disadvantage of audible alarms is that they may make the wearer overly conspicuous and self-conscious.
  • the very purpose of the device is to provide assistance to a person who has hearing difficulties. Providing the user with more external sounds, which he may not hear clearly, can have the unwanted effect of generating confusion and irritation.
  • a device for aiding a person having a hearing impairment comprising: a microphone for converting ambient sounds and commands, including voice commands and other audio signals, to electrical signals; signal processing means for processing said electrical signals in accordance with control signals; means for transmitting processed signals to said person; and command recognition means coupled to said microphone for recognizing said voice commands and wherein said recognition means generates said control signals.
  • a device for aiding a hearing impaired person comprising: an external section worn by said person; and an internal section implanted in said person; said external section including a microphone receiving audio signals and converting them into received electrical signals, signal processing means for processing signals into stimulation signals, transmitting means for transmitting said stimulation signals to said internal section, a battery for generating power to said external section, and means for reporting a status of said battery; said reporting means including monitoring means for monitoring said battery, signal generating means coupled to said monitoring for generating battery status signals indicative of said status and means for combining said battery status signals and said stimulation signals for indicating to said person said battery status.
  • a hearing aid system comprising: means for receiving ambient and command signals and converting said signals into electrical signals; means for separating said electric signals into audio signals and command signals; means for processing said audio signals to generate audio stimulating signals; means for controlling said processing signals in accordance with said command signals; and means for transmitting said stimulating signals to the cochlear nerve of a patient.
  • a cochlear implant system comprising: means for sensing ambient sounds and generating in response first electrical signals; event means for sensing events other than said ambient sounds and generating in response second electrical signals; means for generating processed signals corresponding to said first and second electrical signals; and stimulating electrodes for applying said processed signals to an auditory nerve so that the patient can perceive said ambient sounds and receive information regarding said events.
  • Fig. 1 is a block diagram of a prior art device
  • Fig. 2 is a block diagram of a device according to a first embodiment of the invention
  • Fig. 3 is a block diagram of the command recognition module of Fig. 2
  • Fig. 4 is a block diagram of a second embodiment of the invention
  • Fig. 5 shows the programming information contained in the memory of the device from Fig. 4
  • Fig. 6 i.s a block diagram of a cochlear implant constructed in accordance with a third embodiment of the invention
  • Fig. 7 is a block diagram of a cochlear implant constructed in accordance with a fourth embodiment of the invention
  • Fig. 8 is a schematic diagram of the elements of a two-part cochlear implant system constructed in accordance with the invention
  • Fig. 9 is a schematic diagram o the elements of a completely implanted cochlear system constructed in accordance with the invention.
  • a typical prior art device 10 includes an external section 12 and an internal section 14.
  • the external section 12 includes a microphone 16 which picks up ambient sounds and converts them to corresponding electrical signals on line 18.
  • Line 18 is connected to a manual volume controller 20 shown diagrammatically as a potentiometer.
  • the volume controller output 22 is fed in parallel to a first and a second converter 24, 26 respectively.
  • Each of these converters 24, 26 convert the received signal into cochlea stimulating signals, using certain preselected criteria. For example, converter 24 may perform the conversion using a criteria which is best suited for signals in a crowded room whereas converter 26 may perform a conversion more suitable for sounds in a more intimate, one-to-one conversation.
  • a manual switch 28 is used by the person to select the converter most suitable for a particular environment.
  • the converted signals selected by switch 28 are fed to a transmitter 27 to be sent to internal section 14.
  • Internal section 14 includes a receiver 30, a signal generator 32 and a stimulator electrode 34.
  • the signals from receiver 30 are transformed into suitable cochlea stimulation signals by signal generator 32. These stimulation signals are then transmitted to electrode 34 for stimulating the cochlea.
  • the system may include other components, such as a battery 36 used to provide power to the subassemblies of section 12.
  • a battery test switch 38 In order to check whether the battery is depleted or not, the person closes a battery test switch 38. This allows current to flow from battery 36 to a LED 40. When the battery 36 is low, the LED 40 will be very dim thus indicating that the battery is depleted and should be replaced.
  • this arrangement is disadvantageous in that it has several manual components, such as switches 28 and 38 as well as LED 40, which make it bulky and difficult to operate, especially if hidden in clothing.
  • the device cannot be used by a person who is so incapacitated that he cannot use his fingers.
  • An improved device 1 10 constructed in accordance with one embodiment of this invention is shown in Fig. 2.
  • Device 1 10 includes an external section 1 12 and an internal section which has been omitted since it is preferably identical to the section 14 in Fig. 1. Most of the time, the external section 1 12 operates in the same manner as external section 12 of Fig. 1. More specifically, a microphone 1 16 picks up ambient sounds and converts them into corresponding electrical signals on line 1 18. After amplification by amplifier 120, the amplified signals are fed in parallel to two converters 124, 126. An electronic switch 128 is used to select the output of one of the converters and feed the same to transmitter 127. Power to the whole section 1 12 is provided by a battery 136. In addition, section 1 1 2 further includes a command recognition module 142 which also receives the signals generated by microphone 1 1 6. Module 142 is set up to recognise a plurality of oral commands received from the user via the microphone 1 1 6. These commands are used to control the operation of the section 1 12.
  • the module 142 includes a memory 143 (shown in Fig. 3) which contains a list of acceptable commands. These commands may include, for example, the following: VOLUME UP VOLUME DOWN
  • the module 142 further includes a microprocessor 144, a speech recognition circuit 146 and a demultiplexer 148.
  • the electrical signals from microphone 1 1 6 are monitored and converted into digital form by speech recognition circuit 146.
  • the microprocessor 144 continuously monitors the signals from the circuit 146 and compares them with a list of commands from memory 143. When a set of signals is recognized as a command by microprocessor 144, the microprocessor issues an appropriate command for controlling the operation of section 1 12. For example, when the user utters the commands VOLUME UP or VOLUME DOWN, microprocessor 144 issues a corresponding control signal to the amplifier 120 on line 1 50 to raise or Iower its amplification. If the command CONVERTER A or CONVERTER B is received and recognized, the microprocessor 144 issues a control signal on line 1 52 to electronic switch 1 28 to select the appropriate converter 1 24 or 1 26.
  • section 1 12 includes a battery monitor 1 54, an oscillator 1 56, a control gate 1 58 enabled by a control line 1 60, and a mixer 1 62.
  • the monitor 154 generates an output indicative of the status of the battery 136 (i.e., whether the battery output is above or below a certain threshold, or by using other criteria indicative of the status of the battery). This output is used to control gate 158.
  • An oscillating signal of a particular frequency is generated by oscillator 156 and fed to gate 158.
  • the microprocessor 144 When the BATTERY command is received and recognized, the microprocessor 144 generates an output signal for a preselected time period on line 160 to gate 158. For the period of time that the control signal is on line 160, the gate 158 allows the output of oscillator 156 to propagate to mixer 162, if the monitor 154 indicates that the battery is getting weak or non-operational. As long as the battery 136 is operational or its output is found acceptable by the monitor 154, gate 158 is disabled regardless of the status of line 160. If the battery is found unacceptable, the mixer receives the output of oscillator 156 and superimposes this signal on the signals from the microphone 1 16.
  • the monitor 154 may be used to control the oscillator output directly, for example, by changing its frequency or output amplitude.
  • the commands are stored in memory 143 during a training period, during which the user is asked to voice various commands. Since the voice characteristics of various users are unique or distinctive, the command recognizing module 140 is able to recognize and respond to commands from the user, while similar words from other persons during incidental conversations are ignored. Altematively, the commands can be selected to be specific words, syllables and/or numbers which are not normally used in conversation.
  • a special command may be assigned to 'wake up' the module 140. Unless this 'wake up' command is received first, the module 140 ignores all signals from the microphone 1 16.
  • the embodiment of Fig. 4 pertains to a more advanced device 210 having an external section 212.
  • the signals from a microphone 216 are fed to an A/D converter 270 and the output of the converter 270 is fed to a digital signal processor 272.
  • the signal processor 272 includes programming for performing several functions Iisted in Fig. 5. These functions include the two conversions, conversion 224, and conversion 226, as discussed with respect to Figs 1 and 2.
  • the digital signal processor 272 further includes a command recognition function 240 for recognizing commands by the user a s described above, as well as a battery check 254 and an oscillator function 256.
  • the battery check 254 checks the battery 236, and if necessary, enables the oscillator 256.
  • the output of the oscillator is fed to a mixer 262.
  • the system includes a speech module 310, a microphone 312, a speech processor 314 and a microprocessor 316.
  • the module 310 is coupled to a stimulation delivery means 318.
  • the microphone 312 detects ambient sounds and generates corresponding electrical signals. Under the control of the microprocessor 316, these signals are processed by the speech processor 314 which generates processed signals called "tokens" in accordance with a predetermined algorithm. The processed signals are then provided to the stimulation delivery system 318, as described more fully below in Figs. 8 and 9.
  • Power for the module is provided by a battery and power supply circuitry 336.
  • the battery In the case of a totally implanted device the battery is implanted and is rechargeable by means of a transcutaneous link. In the case of a system which is not totally implantable, as shown in Fig. 8, the battery is housed in the external unit.
  • the speech processor 314 performs such functions as anti-aliasing filtering, analog-to-digital conversion, feature extraction and so on.
  • a cochlear implant system is described for example, in U.S. Patent No. 4,532,930, which is incorporated herein by reference.
  • the system further includes one or more of the following elements: an ambient sensor 320, a command handset 323, a command decoder 324, an analog-to-digital converter 326, a clock 328, a message source 330 and a summer 303.
  • the message source 330 shown in Fig. 6 consists of message RAM 306 and a speech and tome synthesizer 304 for recording and generating speech signals.
  • the additional components are used to provide various information to the patient which was not directly available to him before.
  • the simplest such information is that provided by the clock
  • this clock may be a separate timing device, preferably it is derived from the same clock that is also used to provide the basic clock signals for the microprocessor 316.
  • the clock 328 is also used to provide the patient with an indication of the current time.
  • the clock 328 makes available to the microprocessor 316 the time when requested, either on demand or periodically, by the microprocessor.
  • the time check may be perceived by the user as, for example, "beeps". With reference to Fig. 6, a beep may be generated on the hour by the clock flagging the microprocessor at that time.
  • the message source 330 requests the message source to generate a tone by means of speech synthesizer 304.
  • the tone is fed via connection 302 to the summer 303 where it is mixed with the audio signal from the microphone 312.
  • the combined audio signal is processed by speech processor 314 and delivered to theuser who perceives both the normal hearing information and the time-check tone as a superimposed beep.
  • beeps may be generated according to a grandfather-clock-like scheme with a particular sequence of tones sounding on the quarter hour or other time interval.
  • the memory source 330 may be used to generate a plurality of word messages rather than tones, with each message corresponding to a particular time. For example, one such message may be the spoken words "IT IS ONE PM".
  • the words "IT IS ...PM” would be stored in the message RAM 306.
  • the microprocessor 316 using for example a lockup table retrieves the message an insert a speech synthesiser derived word for the hour to produce the string of words 'IT IS ONE PM", the spoken message is then transmitted via connection 302 to the summer 303 and processed and delivered to the user.
  • a more efficient mode is to store and synthesize tokens of post-processed data rather than pre-processed audio signals.
  • the message source 330A consists of a token RAM 310A and a token synthesizer 308A.
  • the token RAM 310A is used to store various tokens.
  • the tokens are generated by the speech processor 314 an correspond to the messages stored in RAM 310.
  • the token synthesizer 308A is used for generating tokens corresponding to parts of simple, often repetitively structured phrases, e.g., those of a talking clock.
  • the summer 303 of Fig. 6 is omitted and a level adjustment-and-interleaving circuit 332 is provided for combining tokens corresponding to external speech with tokens from the message source 330A.
  • the messages from source 330A correspond to the appropriate spoken time-check messages however they consist of signals which can be conveyed directly to the stimulation delivery module 318.
  • the microprocessor instructs the message source 330A to issue the appropriate message token either from the token RAM 310A or token synthesizer 308A and to send the same to the interleaving circuit 332.
  • This circuit interleaves the tokens from the message source 330A with the tokens from the speech processor 314 and sends the combined processed signals for stimulation by delivery system 318.
  • the interleaving module superimposes the information derived from the message source 330A with that from the speech processor 314 so that the user can continue to partake in a conversation or listen to the radio, etc. while also hearing the private message, without loss of continuity.
  • the combined signals are then applied to the nerve of the patient.
  • the command handset 323 is provided for this purpose. It generates a signal, for example a radio ⁇ frequency transmission, which is detected by the command decoder 324 and converted to a digital form that consists of a microprocessor instruction.
  • the command handset 323 may include of one or more keys, depending on the range of the patient's required command repertoire. The simplest command may be an on/off command.
  • the command handset 323 is provided with a simple switch (not shown) which is activated by the patient to turn the timing feature in or off.
  • the command handset is provided with a keypad and a display screen as discussed below.
  • Another function to be performed by the device is to store and selectively retrieve various messages and data such as reminder notes, telephone numbers, addresses and so on.
  • This information may be entered via the remote control keypad and stored into message source 330 or 330A after appropriate conversion by the token synthesizer. The patent may then retrieve and "hear" this information when demanded by means of the command handset 323.
  • control handset 323 As an example of the use of the control handset 323 to store the user's messages, suppose that it is desired to store the phone number of a friend. The user enters a command "Record Message" by means of the control handset 323. With reference to Fig. 7, this command is transmitted by the command handset 323 to the command decoder 324. The command decoder 324 decodes the command and informs the microprocessor 316 that subsequent microphone input is to be recorded. The microprocessor buffers the tokens received from the speech processor 314 and passes them to the message source 330A with an instruction or the memorandum tokens to be recorded.
  • the command decoder 324 flags the microprocessor 316 that a command has been received and acting on the command the microprocessor 316 terminates the recording.
  • the microprocessor 316 then has the message source 330A issue the message "Message Recorded, Enter Message's Prompt".
  • the user then types in a short phrase or mnemonic that he wishes to retrieve the phone number by, for example, "Peter's Phone
  • the user may recall the phone number at a later time b typing "Recall Message” and then selecting the message's prompt by means of the display screen of the command handset 323.
  • Messages and commands may also be entered by the patient (or another person) via microphone 312.
  • the device must differentiate between commands/data from the patient and normal speech. This may be accomplished by activating a key on the command handset 323 prior to the command/data.
  • the command decoder 324 may be used to recognise data received from the microphone 310 via connection 301 (Fig. 6) rather than the command handset 323. If a certain code word/phrase from the microphone is recognized, the command recognition unit flags the microprocessor that following sounds contain data to be processed and stored in the message source 330, 330A.
  • the command decoder 324 may incorporate a speech recognition algorithm to recognize the wearer's voice, thereby further differentiating between ambient speech and commands and preventing inadvertent programming by unauthorised persons.
  • the command decoder 324 receives the electrical signals from microphone 312 via connection 31 9 and transmits recognized commands to microprocessor 31 6 via a bus 324A.
  • the speech recognition system As an example of the use of the speech recognition system to store the user's messages, suppose that it is desired to store the phone number of a friend. The user utters the command "Record Message". With reference to Fig. 7, this utterance is transduced by microphone 312 and conveyed by means of connection 31 9 to the command decoder 324.
  • the command decoder 324 recognises the command and informs the microprocessor 316 that subsequent microphone input is to be recorded.
  • the microprocessor 316 buffers the tokens received from the speech processor 314 and passes them to the message source 330A with an instruction for the memorandum tokens to be recorded.
  • the command decoder 324 then flags the microprocessor that a command has been received and acting on the command the microprocessor 31 6 terminates the recording.
  • the microprocessor 31 6 then has the message source issue the message "Message Recorded, Enter Message's Prompt".
  • the user then enters a phrase that he wishes to retrieve the phone number by, for example "Peter's Phone Number” and then the instruction "Prompt Ends”. Once this has been done the user may recall the phone number at a later time by uttering "Recall Message”.
  • the message source will then read through the list of message prompts until the user utters the command "Select" at which point the selected message will be recalled.
  • Other information may be transmitted in this manner to the patient as well.
  • the sensor 320 may be provided, which may be, for instance, a temperature sensor arranged and constructed to sense the subcutaneous temperature of the patient. To invoke thus function, the patient may request a temperature reading either by spoken word, or through the command handset 323. The sensor 320 generates an analog signal indicative of temperature and this signal is fed to the analog/digital converter 326. The resulting digital data is logged by the microprocessor 316.
  • the microprocessor 316 then requests an appropriate message from the message source 330A and the necessity tokens are conveyed to the level adjustment and interleaving nit 332 and thence to the stimulation and delivery module 318 which delivers stimulation to the patient.
  • appropriate messages are provided to summer 303.
  • other information may be sensed as well using an appropriate sensor in the place of sensor 318. For example, the sensing of the patient's blood pressure, or pulse rate may be facilitated.
  • other types of sensors may also be used for measuring parameters not directly related to the user's physiological condition such as an odometer for measuring walking or jogging distances.
  • the module 310 may also generate internal diagnostic reports. For instance a low battery level alarm can be implemented by any circuitry that provides a digital signal when the battery falls below a set threshold and delivering this signal to the microprocessor.
  • a convenient way of implementing such a facility using the system already depicted in Fig. 7 is to have the microprocessor 316 periodically request of the analog-to-digital converter 326, a power supply reading from power supply 336. If the battery reading is below a bottom limit, the microprocessor 316 will direct a "low battery" message to be conveyed from the message source 330A to the user.
  • the patient may request a status report by depressing certain keys on the control handset 323, or by uttering certain command words.
  • the microprocessor 316 checks the status of its systems, including for example statistical information on error rates, volume levels, battery level, etc and provides a report to the patient by means of the message source 330A.
  • the external portion 340 includes a wearable speech processor housing 342 containing all the elements of the module 310 and command handset 323 of Fig. 6.
  • External portion 340 also includes a microphone 344, and an inductive transmit coil 352.
  • the microphone 344 performs the same function as microphone 312 and can be implemented as a so called behind- the-ear microphone.
  • housing 342 includes a message screen 348 an a plurality of keys 350 provide the functionality of the command handset 323 in Fig. 6.
  • the patient can enter various information or commands on the keys 350 and monitor and confirm the data entered from the keys 350 on screen 348.
  • the screen 348 may display other information from the cochlear implant as well.
  • the housing 342 is connected by cable 351 to the transmit coil 352.
  • the implanted portion 354 of the device includes a receiver housing 356. Included in the housing 356 is a receiver coil 358.
  • a cable 360 extends from housing 356 into the middle ear of the patient terminating in cochlear electrode array 362 disposed adjacent to the basilar membrane 364, in the usual manner.
  • the transmit and receive coils 352, 358 are arranged to provide inductive coupling therebetween.
  • the patient can transmit commands through buttons 350 and receive information either visually on screen 348 or, according to the present invention, as an aural perception through the cochlear electrode array 362.
  • Fig. 9 shows a completely implanted cochlear device 370.
  • the device 370 includes an internal housing 372 including a microphone 374 and an RF coil 376.
  • Cable 360 extends from housing 372 and terminates with an array of electrodes 362 as described above.
  • the device further includes a remote controller 378 which corresponds to the command handset 323 of Figs. 6 or 7.
  • the controller 378 includes an RF coil 380 for communication by RF signals with the implant 372.
  • the 378 also includes a screen 348 and keys 350.
  • the communication between the patient and the cochlear implant device 370 is accomplished by RF or similar means (eg, radar, ultrasound, etc.).
  • the module 310 is disposed in the housing 372, and the command handset 323 is implemented by the remote controller 378.
  • the apparatus of the invention may be used to control the operation of a cochlear implant.

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  • Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • General Health & Medical Sciences (AREA)
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  • Physics & Mathematics (AREA)
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  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
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  • Life Sciences & Earth Sciences (AREA)
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  • Electrotherapy Devices (AREA)

Abstract

Dispositif de prothèse auditive telle qu'un implant cochléaire, qui comporte un microphone (116) destiné à recevoir les sons ambiants, ainsi que des commandes parlées ou vocales, et à convertir lesdits sons en signaux électriques correspondants. Un processeur (142) sépare le signal en signaux de commande et en signaux vocaux. Les signaux vocaux sont transmis au patient de la manière habituelle, tandis que les signaux de commande sont utilisés pour commander certaines fonctions du processeur, telles que la sélection de critères de traitement du contrôle du volume, ou la fourniture d'informations telles que l'état de la pile, l'heure, la température du corps de l'utilisateur et des mémentos ou des notes faits par l'utilisateur. Les messages d'alarme sont automatiquement transmis à l'utilisateur lorsque cela est approprié, tandis que d'autres sont à sa disposition au moment fixé par lui ou sur demande. Ledit système peut être adapté, ce qui permet à l'utilisateur d'enregistrer ses propres messages et d'entrer des commandes soit par un clavier, soit par reconnaissance vocale.
PCT/AU1996/000403 1995-06-28 1996-06-28 Appareil et procede permettant de commander des processeurs vocaux et de fournir des donnees d'entree privees par l'intermediaire desdits processeurs WO1997001314A1 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
AU61826/96A AU6182696A (en) 1995-06-28 1996-06-28 Apparatus for and method of controlling speech processors and for providing private data input via the same
JP50404897A JP2001508667A (ja) 1995-06-28 1996-06-28 音声処理装置を制御する装置及び方法、並びに、個人的なデータを前記音声処理装置に入力するための音声処理制御装置
EP96920635A EP0840581A1 (fr) 1995-06-28 1996-06-28 Appareil et procede permettant de commander des processeurs vocaux et de fournir des donnees d'entree privees par l'intermediaire desdits processeurs

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
AUPCT/AU95/00380 1995-06-28
AU9500380 1995-06-28

Publications (1)

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WO1997001314A1 true WO1997001314A1 (fr) 1997-01-16

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PCT/AU1996/000403 WO1997001314A1 (fr) 1995-06-28 1996-06-28 Appareil et procede permettant de commander des processeurs vocaux et de fournir des donnees d'entree privees par l'intermediaire desdits processeurs

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EP (1) EP0840581A1 (fr)
JP (1) JP2001508667A (fr)
CA (1) CA2224199A1 (fr)
WO (1) WO1997001314A1 (fr)

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US6289247B1 (en) 1998-06-02 2001-09-11 Advanced Bionics Corporation Strategy selector for multichannel cochlear prosthesis
WO2001074278A2 (fr) * 2000-03-31 2001-10-11 Advanced Bionics Corporation Prothese cochleaire totalement implantable, sous-miniature, ayant un nombre important de contacts
EP1293106A1 (fr) * 2000-04-11 2003-03-19 Cochlear Limited Dispositif de controle d'une pile et dispositif de reglage de besoins en courant
EP1320279A1 (fr) * 2002-06-10 2003-06-18 Phonak Ag Procédé de traitement de données d'une prothèse auditive et prothèse auditive
JP2004523136A (ja) * 2001-01-23 2004-07-29 フォーナック　アーゲー 通信方法及び聴音装置システム
US6842647B1 (en) 2000-10-20 2005-01-11 Advanced Bionics Corporation Implantable neural stimulator system including remote control unit for use therewith
WO2005055579A1 (fr) * 2003-12-02 2005-06-16 Lynne Moody Systeme de production de telepathie artificielle
DE102004031981A1 (de) * 2004-07-01 2005-11-17 Siemens Audiologische Technik Gmbh Terminplaner
US7149319B2 (en) * 2001-01-23 2006-12-12 Phonak Ag Telecommunication system, speech recognizer, and terminal, and method for adjusting capacity for vocal commanding
WO2007052186A2 (fr) 2005-11-01 2007-05-10 Koninklijke Philips Electronics N.V. Technique de reglage d'un dispositif de prothese auditive, systeme de prothese auditive et dispositif de prothese auditive
US7292891B2 (en) 2001-08-20 2007-11-06 Advanced Bionics Corporation BioNet for bilateral cochlear implant systems
US7412288B2 (en) 2004-05-10 2008-08-12 Phonak Ag Text to speech conversion in hearing systems
WO2009127014A1 (fr) 2008-04-17 2009-10-22 Cochlear Limited Processeur sonore pour un implant médical
EP1624722A3 (fr) * 2004-08-02 2010-01-13 Siemens Audiologische Technik GmbH Prothèse auditive avec horloge parlante
JP2010525755A (ja) * 2007-04-25 2010-07-22 ダニエル・アール・シュメイアー ユーザプログラム可能聴覚補助デバイス
WO2011008162A1 (fr) * 2008-10-10 2011-01-20 Milux Holding S.A. Système de commande vocale pour implant
WO2011015673A2 (fr) 2010-11-08 2011-02-10 Advanced Bionics Ag Instrument auditif et son procédé de fonctionnement
WO2011095229A1 (fr) 2010-02-08 2011-08-11 Advanced Bionics Ag Aide auditive entièrement implantable
US8170677B2 (en) 2005-04-13 2012-05-01 Cochlear Limited Recording and retrieval of sound data in a hearing prosthesis
US8588911B2 (en) 2011-09-21 2013-11-19 Cochlear Limited Medical implant with current leakage circuitry
US8634918B2 (en) 2008-10-09 2014-01-21 Cochlear Limited Medical implant with safety feature
US9238140B2 (en) 2006-08-25 2016-01-19 Cochlear Limited Current leakage detection
US9913050B2 (en) 2015-12-18 2018-03-06 Cochlear Limited Power management features
EP3032845B1 (fr) 2014-12-12 2020-02-05 GN Hearing A/S Dispositif d'aide auditive apte à authentifier une demande de changer un mode de service et procédé associé
US11206496B2 (en) 2014-12-12 2021-12-21 Gn Hearing A/S Hearing device with service mode and related method
US11412333B2 (en) 2017-11-15 2022-08-09 Starkey Laboratories, Inc. Interactive system for hearing devices
US11426592B2 (en) 2015-05-14 2022-08-30 Cochlear Limited Functionality migration

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JP2007333778A (ja) * 2006-06-12 2007-12-27 Toshiichi Shinshi 商品売買システムとそれを実現するためのコンピュータプログラムとその方法

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EP0707433A2 (fr) * 1994-10-14 1996-04-17 Matsushita Electric Industrial Co., Ltd. Prothèse auditive

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EP0707433A2 (fr) * 1994-10-14 1996-04-17 Matsushita Electric Industrial Co., Ltd. Prothèse auditive

Cited By (44)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6289247B1 (en) 1998-06-02 2001-09-11 Advanced Bionics Corporation Strategy selector for multichannel cochlear prosthesis
US6826430B2 (en) 2000-03-31 2004-11-30 Advanced Bionics Corporation High contact count, sub-miniature, fully implantable cochlear prosthesis
WO2001074278A2 (fr) * 2000-03-31 2001-10-11 Advanced Bionics Corporation Prothese cochleaire totalement implantable, sous-miniature, ayant un nombre important de contacts
WO2001074278A3 (fr) * 2000-03-31 2002-06-20 Advanced Bionics Corp Prothese cochleaire totalement implantable, sous-miniature, ayant un nombre important de contacts
US7444185B1 (en) 2000-03-31 2008-10-28 Advanced Bionics, Llc High contact count, sub-miniature, fully implantable cochlear prosthesis
US6980864B2 (en) 2000-03-31 2005-12-27 Advanced Bionics Corporation High contact count, sub-miniature, full implantable cochlear prosthesis
US7627378B2 (en) 2000-04-11 2009-12-01 Cochlear Limited Battery monitor and power demand adjuster
EP1293106A4 (fr) * 2000-04-11 2005-03-16 Cochlear Ltd Dispositif de controle d'une pile et dispositif de reglage de besoins en courant
EP1293106A1 (fr) * 2000-04-11 2003-03-19 Cochlear Limited Dispositif de controle d'une pile et dispositif de reglage de besoins en courant
US7120500B1 (en) 2000-04-11 2006-10-10 Cochlear Limited Battery monitor and power demand adjuster
US7043304B1 (en) 2000-10-20 2006-05-09 Advanced Bionics Corporation Method of controlling an implantable neural stimulator
US6842647B1 (en) 2000-10-20 2005-01-11 Advanced Bionics Corporation Implantable neural stimulator system including remote control unit for use therewith
JP2004523136A (ja) * 2001-01-23 2004-07-29 フォーナック　アーゲー 通信方法及び聴音装置システム
US7149319B2 (en) * 2001-01-23 2006-12-12 Phonak Ag Telecommunication system, speech recognizer, and terminal, and method for adjusting capacity for vocal commanding
US7292891B2 (en) 2001-08-20 2007-11-06 Advanced Bionics Corporation BioNet for bilateral cochlear implant systems
US7251338B2 (en) 2002-06-10 2007-07-31 Phonak Ag Method for handling data of a hearing device and hearing device
EP1320279A1 (fr) * 2002-06-10 2003-06-18 Phonak Ag Procédé de traitement de données d'une prothèse auditive et prothèse auditive
WO2005055579A1 (fr) * 2003-12-02 2005-06-16 Lynne Moody Systeme de production de telepathie artificielle
US7412288B2 (en) 2004-05-10 2008-08-12 Phonak Ag Text to speech conversion in hearing systems
DE102004031981A1 (de) * 2004-07-01 2005-11-17 Siemens Audiologische Technik Gmbh Terminplaner
EP1624722A3 (fr) * 2004-08-02 2010-01-13 Siemens Audiologische Technik GmbH Prothèse auditive avec horloge parlante
US8170677B2 (en) 2005-04-13 2012-05-01 Cochlear Limited Recording and retrieval of sound data in a hearing prosthesis
WO2007052186A3 (fr) * 2005-11-01 2007-09-07 Koninkl Philips Electronics Nv Technique de reglage d'un dispositif de prothese auditive, systeme de prothese auditive et dispositif de prothese auditive
WO2007052186A2 (fr) 2005-11-01 2007-05-10 Koninklijke Philips Electronics N.V. Technique de reglage d'un dispositif de prothese auditive, systeme de prothese auditive et dispositif de prothese auditive
US9238140B2 (en) 2006-08-25 2016-01-19 Cochlear Limited Current leakage detection
JP2010525755A (ja) * 2007-04-25 2010-07-22 ダニエル・アール・シュメイアー ユーザプログラム可能聴覚補助デバイス
EP2277326A4 (fr) * 2008-04-17 2012-07-18 Cochlear Ltd Processeur sonore pour un implant médical
EP2277326A1 (fr) * 2008-04-17 2011-01-26 Cochlear Limited Processeur sonore pour un implant médical
WO2009127014A1 (fr) 2008-04-17 2009-10-22 Cochlear Limited Processeur sonore pour un implant médical
US8634918B2 (en) 2008-10-09 2014-01-21 Cochlear Limited Medical implant with safety feature
US8838458B2 (en) 2008-10-10 2014-09-16 Peter Forsell Voice control system for an implant
WO2011008162A1 (fr) * 2008-10-10 2011-01-20 Milux Holding S.A. Système de commande vocale pour implant
WO2011095229A1 (fr) 2010-02-08 2011-08-11 Advanced Bionics Ag Aide auditive entièrement implantable
WO2011015673A2 (fr) 2010-11-08 2011-02-10 Advanced Bionics Ag Instrument auditif et son procédé de fonctionnement
US8588911B2 (en) 2011-09-21 2013-11-19 Cochlear Limited Medical implant with current leakage circuitry
EP3032845B1 (fr) 2014-12-12 2020-02-05 GN Hearing A/S Dispositif d'aide auditive apte à authentifier une demande de changer un mode de service et procédé associé
US11206496B2 (en) 2014-12-12 2021-12-21 Gn Hearing A/S Hearing device with service mode and related method
US11546699B2 (en) 2014-12-12 2023-01-03 Gn Hearing A/S Hearing device with service mode and related method
US11426592B2 (en) 2015-05-14 2022-08-30 Cochlear Limited Functionality migration
US10555093B2 (en) 2015-12-18 2020-02-04 Cochlear Limited Power management features
US9913050B2 (en) 2015-12-18 2018-03-06 Cochlear Limited Power management features
US11528565B2 (en) 2015-12-18 2022-12-13 Cochlear Limited Power management features
US12028681B2 (en) 2015-12-18 2024-07-02 Cochlear Limited Power management features
US11412333B2 (en) 2017-11-15 2022-08-09 Starkey Laboratories, Inc. Interactive system for hearing devices

Also Published As

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EP0840581A1 (fr) 1998-05-13
CA2224199A1 (fr) 1997-01-16

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