CA2382039A1 - Multichannel cochlear implant with neural response telemetry - Google Patents
Multichannel cochlear implant with neural response telemetry Download PDFInfo
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- CA2382039A1 CA2382039A1 CA002382039A CA2382039A CA2382039A1 CA 2382039 A1 CA2382039 A1 CA 2382039A1 CA 002382039 A CA002382039 A CA 002382039A CA 2382039 A CA2382039 A CA 2382039A CA 2382039 A1 CA2382039 A1 CA 2382039A1
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- 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
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- 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
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- 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
- A61N1/372—Arrangements in connection with the implantation of stimulators
- A61N1/37211—Means for communicating with stimulators
- A61N1/37252—Details of algorithms or data aspects of communication system, e.g. handshaking, transmitting specific data or segmenting data
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- 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
Abstract
A circuit and method for cochlear implant telemetry where digital data is encoded into an RF signal. The RF signal is applied via a rectifier diode to a first switch matrix S1 and a second switch matrix S2, with S1 being coupled to a first sampling capacitor C1 and S2 being coupled to a second sampling capacitor C2. A local oscillator signal with period T is applied that controls S1 and S2, cyclically coupling C1 and C2 to the RF signal, a first input to a comparator, and ground. The comparator compares the first input to a DC reference voltage. The output of the comparator is then sampled via a flip flop clocked by the local oscillator, with the flip flop outputting a data bit stream representative of the envelope of the RF signal having encoded information.
Claims (54)
1. A data transmission system comprising:
a. a coding unit coupled to a communication channel, that transmits encoded digital information having defined minimum and maximum durations of logical states "low" and "high";
b. a decoding unit coupled to the communication channel, that decodes information received, the decoder comprising:
i. a free running local oscillator LO coupled to an array of sampling capacitors, that effectively samples the information using the LO
frequency, and ii. a circuit coupled to the sampling capacitors, that decodes the information and corrects any mismatch between nominal and actual LO
frequency.
a. a coding unit coupled to a communication channel, that transmits encoded digital information having defined minimum and maximum durations of logical states "low" and "high";
b. a decoding unit coupled to the communication channel, that decodes information received, the decoder comprising:
i. a free running local oscillator LO coupled to an array of sampling capacitors, that effectively samples the information using the LO
frequency, and ii. a circuit coupled to the sampling capacitors, that decodes the information and corrects any mismatch between nominal and actual LO
frequency.
2. A data transmission system according to claim 1, wherein the encoded digital information is contained in an RF signal.
3. A data transmission system according to claim 1, for use in a cochlear implant system.
4. A data transmission system according to claim 1, for use in an implantable system for functional electrostimulation.
5. A data decoder system comprising:
a. a decoding unit coupled to a communication channel that decodes information received, the decoder comprising:
i. a free running local oscillator LO coupled to an array of sampling capacitors, that effectively samples the information using the LO
frequency; and ii. a circuit coupled to the sampling capacitors, that decodes the information and corrects any mismatch between nominal and actual LO
frequency.
a. a decoding unit coupled to a communication channel that decodes information received, the decoder comprising:
i. a free running local oscillator LO coupled to an array of sampling capacitors, that effectively samples the information using the LO
frequency; and ii. a circuit coupled to the sampling capacitors, that decodes the information and corrects any mismatch between nominal and actual LO
frequency.
6. A data decoder system according to claim 5, wherein the encoded digital information is contained in an RF signal.
7. A data decoder system according to claim 5, that is used in a cochlear implant system.
8. A data decoder system according to claim 5, that is used in an implantable system for functional electrostimulation.
9. A circuit for detecting the envelope of an input signal, the circuit comprising:
a. a first sampling capacitor C1 and a second sampling capacitor C2, both capacitors coupled to ground;
b. a first switching matrix S1 cyclically coupling C1 to:
i. an input signal via a rectifier diode, the input signal being encoded with digital data, ii. a first input of a comparator, and iii. ground;
c. a second switch matrix S2 cyclically coupling C2 to:
i. the input signal via the rectifier diode, ii. the first input of the comparator, and iii. ground;
d. a local oscillator coupled to S1 and S2, that controls switch matrices S1 and S2, the local oscillator having period T;
e. a dc-reference coupled to a second input of the comparator; and a flip flop coupled to the comparator output, the flip flop being clocked by the local oscillator producing a data bit stream output indicative of the input signal's envelope.
a. a first sampling capacitor C1 and a second sampling capacitor C2, both capacitors coupled to ground;
b. a first switching matrix S1 cyclically coupling C1 to:
i. an input signal via a rectifier diode, the input signal being encoded with digital data, ii. a first input of a comparator, and iii. ground;
c. a second switch matrix S2 cyclically coupling C2 to:
i. the input signal via the rectifier diode, ii. the first input of the comparator, and iii. ground;
d. a local oscillator coupled to S1 and S2, that controls switch matrices S1 and S2, the local oscillator having period T;
e. a dc-reference coupled to a second input of the comparator; and a flip flop coupled to the comparator output, the flip flop being clocked by the local oscillator producing a data bit stream output indicative of the input signal's envelope.
10. A circuit according to claim 9, for detecting the envelope of an input signal in a cochlear implant, wherein the input signal is an RF signal encoded with digital information.
11. The circuit according to claim 9, wherein a first logical state is encoded by the sequence "RF-carrier off" followed by "RF-carrier on," and a second logical state is encoded by the sequence "RF-carrier on" followed by "RF-carrier off."
12. The circuit according to claim 11, wherein the RF input signal is encoded using Amplitude Shift Keying Modulation, the digital data employing a self-clocking bit format.
13. The circuit according to claim 11, wherein C1 and C2 are sequentially and cyclically coupled via the switching matrices to:
a. the input signal via the rectifier diode, for time duration T/2 (phase D), b. the comparator for time duration T (phase C), and c. ground for time duration T/2 (phase G); S2's switching sequence being offset from S1's switching sequence by a phase shift of T.
a. the input signal via the rectifier diode, for time duration T/2 (phase D), b. the comparator for time duration T (phase C), and c. ground for time duration T/2 (phase G); S2's switching sequence being offset from S1's switching sequence by a phase shift of T.
14. The circuit according to claim 13, wherein the clock of the flip flop is activated at the end of phases C on the negative slope of the local oscillator.
15. A method for data telemetry, the method comprising:
a. encoding digital data into an input signal;
b. applying the input signal via a rectifier diode to a first switch matrix S1 and a second switch matrix S2, S1 being coupled to a first sampling capacitor C1, S2 being coupled to a second sampling capacitor C2;
c. applying a local oscillator signal with period T that controls S1 and S2, so as to cyclically couple C1 and C2 to:
i. the input signal, ii. a first input to a comparator, and iii. ground;
d. applying a DC reference voltage to the second input of the comparator; and e. sampling the output of the comparator via a flip flop clocked by the local oscillator, the flip flop outputting a data bit stream, the data bit stream representative of the input signal's envelope having encoded information.
a. encoding digital data into an input signal;
b. applying the input signal via a rectifier diode to a first switch matrix S1 and a second switch matrix S2, S1 being coupled to a first sampling capacitor C1, S2 being coupled to a second sampling capacitor C2;
c. applying a local oscillator signal with period T that controls S1 and S2, so as to cyclically couple C1 and C2 to:
i. the input signal, ii. a first input to a comparator, and iii. ground;
d. applying a DC reference voltage to the second input of the comparator; and e. sampling the output of the comparator via a flip flop clocked by the local oscillator, the flip flop outputting a data bit stream, the data bit stream representative of the input signal's envelope having encoded information.
16. A method according to claim 15, for detecting the envelope of an input signal in a cochlear implant, wherein the input signal is an RF signal encoded with digital information.
17. A method according to claim 15, for data telemetry in a cochlear implant.
18. The method according to claim 15, wherein in the input signal, a first logical state is encoded by the sequence "RF-carrier off" followed by "RF-carrier on," and a second logical state is encoded by the sequence "RF-carrier on"
followed by "RF-carrier off."
followed by "RF-carrier off."
19. The method according to claim 18, wherein the input signal contains special bit formats, such that the signal can be switched on or off for longer durations.
20. The method according to claim 18, wherein the input signal can be switched on or off for a duration of 3B/2, B being the bit duration.
21. The method according to claim 18, wherein the RF signal is encoded using Amplitude Shift Keying Modulation, the digital data employing a self-clocking bit format.
22. The method according to claim 15, wherein the sampling capacitors C1 and C2 are sequentially and cyclically coupled via the switching matrices to:
a. the input signal for time duration T/2 (phase D), b. the 1st input of the comparator for time duration T (phase C), and c. to ground for time duration T/2 (phase G); S2's switching sequence being offset from S1's switching sequence by a phase shift of T.
a. the input signal for time duration T/2 (phase D), b. the 1st input of the comparator for time duration T (phase C), and c. to ground for time duration T/2 (phase G); S2's switching sequence being offset from S1's switching sequence by a phase shift of T.
23. The method according to claim 15, further comprising decoding the data bit stream.
24. The method according to claim 23, wherein the decoding includes distinguishing four different data bit stream states, the data bit stream states comprising:
a. a "short low" L1 defined by a data bit stream pattern of 0 or 00;
b. a "short high" H1 defined by a data bit stream pattern of 11 or 111;
c. a "long low" L2 defined by a data bit stream pattern of 000 or 0000; and d. a "long high" H2 defined by a data bit stream pattern of 1111 or 11111.
a. a "short low" L1 defined by a data bit stream pattern of 0 or 00;
b. a "short high" H1 defined by a data bit stream pattern of 11 or 111;
c. a "long low" L2 defined by a data bit stream pattern of 000 or 0000; and d. a "long high" H2 defined by a data bit stream pattern of 1111 or 11111.
25. The method according to claim 24, wherein decoding the data bit stream includes distinguishing two additional bit states, the bit states comprising:
a. an "extra long low" L3 defined by a data bit stream pattern of 00000 or 000000; and b. an "extra long high" H3 defined by a data bit stream pattern of 111111 or 1111111.
a. an "extra long low" L3 defined by a data bit stream pattern of 00000 or 000000; and b. an "extra long high" H3 defined by a data bit stream pattern of 111111 or 1111111.
26. The method according to claim 25, wherein decoding the bit stream includes distinguishing triplet sequences, the triplet sequences comprising:
a. a starting short state L1 or H1;
b. a sequence of strictly alternating states L3 or H3;
c. terminating short state L1 or H1.
a. a starting short state L1 or H1;
b. a sequence of strictly alternating states L3 or H3;
c. terminating short state L1 or H1.
27. The method according to claim 26, wherein the triplet sequence data word can be used for data control and synchronization.
28. The method according to claim 26 wherein the data word formats allow high rate stimulation strategies based on sign-correlated, simultaneous stimulation pulses.
29. The method according to claim 26, wherein data telemetry is achieved by data word formats comprising:
a. a starting triplet sequence;
b. a particular number of information bits with self-clocking format; and c. a terminating triplet sequence.
a. a starting triplet sequence;
b. a particular number of information bits with self-clocking format; and c. a terminating triplet sequence.
30. The method according to claim 29, wherein the encoded information allows the following active stimulation modes:
a. stimulation with sign-correlated biphasic, symmetrical pulses;
b. stimulation with sign-correlated triphasic, symmetrical pulses;
and c. stimulation with sign-correlated triphasic pulses.
a. stimulation with sign-correlated biphasic, symmetrical pulses;
b. stimulation with sign-correlated triphasic, symmetrical pulses;
and c. stimulation with sign-correlated triphasic pulses.
31. A method of employing high-rate pulsatile stimulation comprising a. recieving encoded information;
a. decoding the information ;and b. applying stimulation modes based on the decoded information, the stimulation modes comprising:
i. sign-correlated biphasic, symmetrical pulses;
ii. sign-correlated triphasic, symmetrical pulses; and iii. sign-correlated triphasic pulses.
a. decoding the information ;and b. applying stimulation modes based on the decoded information, the stimulation modes comprising:
i. sign-correlated biphasic, symmetrical pulses;
ii. sign-correlated triphasic, symmetrical pulses; and iii. sign-correlated triphasic pulses.
32. A circuit for generating sign-correlated simultaneous pulsatile comprising:
a. a plurality of circuit paths coupled in parallel between a voltage rail and ground, each circuit path comprising an electrode coupled to two current sources having opposite sign;
b. a remote ground electrode coupled to the voltage rail via a first switch, the remote ground electrode further coupled to ground via a second switch;
wherein stimulation is achieved by activating all current sources of the same sign and switching the remote ground electrode to create a current in the remote ground electrode equal to the sum of all single electrode currents.
a. a plurality of circuit paths coupled in parallel between a voltage rail and ground, each circuit path comprising an electrode coupled to two current sources having opposite sign;
b. a remote ground electrode coupled to the voltage rail via a first switch, the remote ground electrode further coupled to ground via a second switch;
wherein stimulation is achieved by activating all current sources of the same sign and switching the remote ground electrode to create a current in the remote ground electrode equal to the sum of all single electrode currents.
33. A circuit according to claim 32, that generates sign-correlated simultaneous pulsatile in a cochlear implant.
34. A circuit according to claim 32 that can generate the following sign-correlated simultaneous pulsatile:
a. sign-correlated biphasic, symmetrical pulses;
b. sign-correlated triphasic, symmetrical pulses;
c. and sign-correlated triphasic pulses.
a. sign-correlated biphasic, symmetrical pulses;
b. sign-correlated triphasic, symmetrical pulses;
c. and sign-correlated triphasic pulses.
35. A method of generating sign-correlated simultaneous pulsatile stimuli comprising:
a. simultaneously applying current of same sign to a plurality of electrodes Ei; and b. switching a remote ground electrode to create a current in the remote ground electrode equal to the sum of absolute values of all single electrode Ei currents.
a. simultaneously applying current of same sign to a plurality of electrodes Ei; and b. switching a remote ground electrode to create a current in the remote ground electrode equal to the sum of absolute values of all single electrode Ei currents.
36. A method according to claim 35 wherein simultaneously applying current of same sign to a plurality of electrodes Ei, each electrode is coupled via a switch to either a first or second current source, the second current source having the opposite sign as the first current source.
37. A method according to claim 35, wherein the acoustic nerve is stimulated by the sign-correlated simultaneous pulsatile stimuli.
38. A method according to claim 35, that generates sign-correlated simultaneous pulsatile stimuli in a cochlear implant.
39. A method according to claim 35, wherein creating the current in the remote ground electrode, the following pulses can be created:
a. sign-correlated biphasic, symmetrical pulses;
b. sign-correlated triphasic, symmetrical pulses; and c. sign-correlated triphasic pulses.
a. sign-correlated biphasic, symmetrical pulses;
b. sign-correlated triphasic, symmetrical pulses; and c. sign-correlated triphasic pulses.
40. A circuit for measurement of electrically evoked action potentials comprising:
a. a measurement electrode coupled to a first input of a differential amplifier via a first double switch;
b. a reference electrode coupled to a second input of the differential amplifier via the first double switch;
c. an output of the differential amplifier coupled to an input of a sigma-delta modulator;
d. an output of the the sigma-delta modulator coupled to memory;
wherein during measurement, the electrically evoked action potential is amplified and converted to a high frequency one bit sigma-delta sequence, the sequence being stored in the implant's memory.
a. a measurement electrode coupled to a first input of a differential amplifier via a first double switch;
b. a reference electrode coupled to a second input of the differential amplifier via the first double switch;
c. an output of the differential amplifier coupled to an input of a sigma-delta modulator;
d. an output of the the sigma-delta modulator coupled to memory;
wherein during measurement, the electrically evoked action potential is amplified and converted to a high frequency one bit sigma-delta sequence, the sequence being stored in the implant's memory.
41. A circuit for measurement according to claim 40, wherein the memory is RAM.
42. A circuit for measurement according to claim 40 that measures electrically evoked action potentials in a cochlear implant.
43. A circuit for measurement according to claim 40, further comprising:
a. coupling the ouput of the differential amplifier to a sampling capacitor via a second double switch; and b. the sampling capacitor coupled across the input of the sigma-delta modulator, that samples the electrically evoked action potentials at select times.
a. coupling the ouput of the differential amplifier to a sampling capacitor via a second double switch; and b. the sampling capacitor coupled across the input of the sigma-delta modulator, that samples the electrically evoked action potentials at select times.
44. A circuit for measurement according to claim 43, further comprising:
a. coupling the sampling capacitor to the first coupling capacitor and a stimulation reference electrodes via a third double switch, that allows measuring of stimulus artifacts.
a. coupling the sampling capacitor to the first coupling capacitor and a stimulation reference electrodes via a third double switch, that allows measuring of stimulus artifacts.
45. A method for measurement of electrically evoked action potentials comprising:
a. sampling an input signal across a measurement electrode and a reference electrode, the electrode and reference electrode being coupled in parallel, producing a sampled signal;
b. amplifying the sampled signal with an amplifier to produce an amplified analog signal;
c. digitizing the amplified analog signal with a sigma-delta modulator to produce a digitized signal;
d. outputting the digitized signal to memory; wherein during measurement, the electrically evoked action potential is amplified and converted to a high frequency one bit sigma-delta sequence, the sequence being stored in memory.
a. sampling an input signal across a measurement electrode and a reference electrode, the electrode and reference electrode being coupled in parallel, producing a sampled signal;
b. amplifying the sampled signal with an amplifier to produce an amplified analog signal;
c. digitizing the amplified analog signal with a sigma-delta modulator to produce a digitized signal;
d. outputting the digitized signal to memory; wherein during measurement, the electrically evoked action potential is amplified and converted to a high frequency one bit sigma-delta sequence, the sequence being stored in memory.
46. A method according to claim 45, wherein the input signal is sampled with a first double switch.
47. A method according to claim 45, wherein the amplified analog signal is sampled and held before being digitized.
48. A method according to claim 45, wherein the amplifier is a differential amplifier.
49. A method according to claim 48, wherein the measurement electrode and the reference electrode are coupled to the differential amplifier via coupling capacitors.
50. A method according to claim 45, further comprising sending the sigma-delta data sequence from memory to outside by load modulation, allowing reconstruction of the electrically evoked action potential signal from the digitized data to be achieved off-line.
51. A method according to claim 45, that measures electrically evoked action potentials in a cochlear implant.
52. A method for measurement of stimulus artifacts comprising:
a. sampling an input voltage across a measurement electrode and a reference electrode with a sampling capacitor to create a sampled input;
b. outputting, at a programmable time instant, the sampled input to a sigma-delta modulator via a switch to produce a sigma-delta data sequence;
c. outputting the sigma-delta data sequence to memory.
a. sampling an input voltage across a measurement electrode and a reference electrode with a sampling capacitor to create a sampled input;
b. outputting, at a programmable time instant, the sampled input to a sigma-delta modulator via a switch to produce a sigma-delta data sequence;
c. outputting the sigma-delta data sequence to memory.
53. A method according to claim 52, further comprising sending the sigma-delta data sequence from memory to outside by load modulation, allowing reconstruction of the electrically evoked action potential signal from the digitized data to be achieved off-line.
54. A method according to claim 52 that measures stimulus artifacts in a cochlear implant.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US14479999P | 1999-07-21 | 1999-07-21 | |
| US60/144,799 | 1999-07-21 | ||
| PCT/IB2000/001151 WO2001006810A2 (en) | 1999-07-21 | 2000-07-21 | Multichannel cochlear implant with neural response telemetry |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2382039A1 true CA2382039A1 (en) | 2001-01-25 |
| CA2382039C CA2382039C (en) | 2009-12-15 |
Family
ID=22510193
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002382039A Expired - Lifetime CA2382039C (en) | 1999-07-21 | 2000-07-21 | Multichannel cochlear implant with neural response telemetry |
Country Status (8)
| Country | Link |
|---|---|
| US (2) | US6600955B1 (en) |
| EP (3) | EP1351554B1 (en) |
| AT (2) | ATE265796T1 (en) |
| AU (1) | AU769596B2 (en) |
| CA (1) | CA2382039C (en) |
| DE (2) | DE60010273T2 (en) |
| ES (2) | ES2358189T3 (en) |
| WO (1) | WO2001006810A2 (en) |
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