US3692959A - Digital hearing aid gain analyzer - Google Patents
Digital hearing aid gain analyzer Download PDFInfo
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- US3692959A US3692959A US84823A US3692959DA US3692959A US 3692959 A US3692959 A US 3692959A US 84823 A US84823 A US 84823A US 3692959D A US3692959D A US 3692959DA US 3692959 A US3692959 A US 3692959A
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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
- H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
Definitions
- the present invention relates to gain analyzers and especially to gain analyzers for analyzing the gain of hearing aids displaying the gain in digital form.
- the present invention relates to a gain analyzer for hearing aids, or the like, having a digital display.
- a sine wave generator or oscillator is provided which can generate a sine wave over a wide range of frequencies in predetermined steps which waves are converted to sound by a transducer located in an anechoic chamber.
- the hearing aid to be tested is placed in a chamber with its receiver end connected to a microphone pickup in a 2 cubic centimeter coupler which coupler simulates the cavity of a human ear and isolates the microphone from the chamber. With the hearing aid turned on the microphone will pick up signals generated by a sine wave oscillator.
- Analog-to-digital conversion circuitry converts the signals from the hearing aid to digital signals indicative of the gain of the hearing aid. The digital signals are counted and displayed on Nixie tubes in digital form.
- FIG. 1 is a perspective of a gain analyzer illustrating the inputs and digital displays
- FIG. 2 is a block diagram of one embodiment of the electrical components of the present invention.
- FIG. 1 a gain analyzer is illustrated in a casing l 1 and having a control panel 12 with an onoff switch 13 and a light 14 to indicate when the apparatus is in an operative position.
- Push-switches l allow the selection of any one of a plurality of frequencies, in this case starting with 250 through 4,000, having steps of 500, 1,000, 1,500, 2,000 and 3,000.
- the control panel also has a digital display output 16 which displays the gain of an amplifier in decibels in digital form for easy reading and has a reset switch 17 and a count switch 18.
- a liftable top 20 allows a hearing aid to be inserted inside an anechoic chamber for testing.
- each of the switches 15 controls the sine wave oscillator 21 to generate a predetermined sine wave frequency which is applied to a calibration 22.
- the calibration board consists of a series of parallel connected adjustable resistors or rheostats each in series with a switch so that each one can be switched and adjusted to assure the correct output level for that frequency.
- TI-Ie signal is next applied to a speaker amplifier 23 where the signal is amplified which amplifier is coupled to a speaker 24 through a coupling capacitor 25.
- Speaker transducer 24 is located in an anechoic chamber 26 and reproduces the sine wave at a predetermined frequency and gain in the chamber 26.
- the chamber 16 may have a hearing aid 27 placed therein with its receiving tube 28 connected to a microphone or similar transducer 30.
- the hearing aid With the hearing aid turned to an on position, the sine wave oscillator operated at a predetermined frequency, the hearing aid will pick up the sound generated in the chamber 26, amplify it, and produce the amplified sound in the sound tube 28 which is picked up by the microphone 30 housed inside a commercially available 2 cubic centimeter coupler which simulates the human ear and also isolates the microphone 30 from the chamber 26.
- Microphone 30 impinges the signal upon a microphone amplifier 31 which amplifies the signal and couples it through a capacitor 32 ro a precision AC rectifier 33.
- the AC rectifier 33 converts the alternating current signal to direct current which direct current may be intermittent in nature.
- the AC rectifier 33 applies the signal to a DC logarithmic amplifier 34, which amplifier provides an amplified output which is a logarithmic function for conversion of linear-to-log, hence decibels, of the input, which signal is then applied to an offset amplifier 35 and then to a wide band voltage controlled oscillator-36.
- the voltage controlled oscillator is one in which the oscillator frequency varies in proportion to the controlled voltage being applied to the oscillator.
- These signals are then applied to a Schmitt trigger 37 which gives fixed output levels for predetermined input levels.
- the output of the Schmitt trigger is applied to the first decade counter 38 which provides one pulse output for each pulse applied to the input decade counter.
- the output of the decade counter is applied to inverter 40 into a second decade counter 41.
- Inverter 40 inverts the signal from a decade counter for the decoder driver 42 which drives a units Nixie tube 43 for displaying the units portion of the output in decibels.
- Second decade counter 41 receives only one input pulse for every 10 input pulses to decade counter 38 and therefore counts in tens.
- the output from the decade counter 41 is applied to a second inverter 44 for inverting the signal and applying to the decoder driver 45 for providing the output for the display Nixie tubes 46 which is a tens unit.
- a reset switch 27 discharges the decade counter for resetting the display tubes for the next frequency test.
- a counting switch 48 is connected to a one-shot or monostable multivibrator 50 which is activated by the count switch 48 and will actuate the monostable multivibrator 50 for gating counting signals to the decade counter 41.
- the monostable or one-shot multivibrator 50 has only one condition of steady state equilibrium in which the circuit can remain for an indefinite period of time and there is one condition of momentary equilibrium in which the circuit remains on for one millisecond period of time. Each time the triggering pulse from the count switch 48 is applied the circuit first switches to the momentary equilibrium condition and then after a finite period of time reverses to the original condition and remains in that condition until another pulse is applied.
- a gate is opened for l millisecond by the monostable to allow counting of pulses from the voltage controlled oscillator to the decade counter.
- the voltage controlled oscillator runs at a 5 digit frequency
- the l millisecond gate allows only the first two digits to be counted, hence increasing the count accuracy 1,000: 1.
- a digital hearing aid gain analyzer which will accept a head worn type hearing aid and measure its gain displaying it in decibels by virtue of Nixie display tubes.
- the power supply for the electronic circuits is not illustrated since it is of course assumed that power supply will be required which may include simple half wave and full wave bridge rectifiers to provide the desired voltages.
- the analog circuitry may comprise the sine wave oscillator 15, a voltage control oscillator 36, a microphone amplifier 31, a precision rectifier 33 and direct current logarithmic amplifier 34 and an offset amplifier 35.
- Sine oscillator is a Wien bridge type which produces a pure sine wave to drive a speaker 24 with pure tone.
- This tone in turn is sensed by the hearing aid 27 to be measured; the gain of the hearing aid is in turn sensed through a microphone 30 and amplified by the microphone amplifier 31.
- This amplified signal is rectified by the precision rectifier circuit 33.
- the output of this rectifier 33 which is a varying minus DC voltage, drives a DC logarithmic amplifier 34 converting a linear voltage into a logarithmic one, hence converting it to decibels.
- DC log amplifier 34 drives the offset amplifier 35 which in turn supplies the voltage controlled oscillator with a voltage comparable to the gain of the hearing aid 27.
- the voltage controlled oscillator 36 is a wide-band complimentary type flip-flop driven by a current source. Its frequency will vary depending upon the gain of the hearing aid.
- the digital displaying counter circuitry enhances a units and tens counter of the binary type. Units to be counted are produced by a voltage control oscillator 37, shaped through a Schmitt trigger 37 and fed into the unit counter 38. The counting time is determined by one-shot multi-vibrator 30 which may be set to a l millisecond time period. Since this is a manual type counter, the reset switch 48 must be operated before the count switch will allow the counter to count.
- the individual circuits used in the present invention are of conventional design and other circuits of the same general type can be utilized as desired. Accordingly this invention is not to be construed as limited to the particular forms disclosed herein since these are to be regarded as illustrative rather than restrictive.
- a gain analyzer apparatus for measuring the gain of audio amplifying devices comprising in combination:
- signal generating means for generating predetermined audio frequencies
- transducer means coupled to said signal generating means and located in said chamber means for producing said audio frequencies in said chamber means
- microphone means located in said chamber means and having means for acoustically coupling the output of an audio amplifying device thereto, whereby said audio amplifying device is adapted to amplifying said audio frequencies in said chamber means and apply said amplified audio frequencies to said microphone means;
- analog to digital conversion means coupled to said microphone means for generating digital signals from the output from said microphone means, said digital signals being indicative of the gain of the amplifying device being analyzed;
- counting means coupled to said analog to digital conversion means for counting digital signals received from said analog to digital conversion means.
- said counting means includes Nixie display tubes for'displaying the counted digital signals as the gain of said amplifying device at a predetermined input frequency.
- said microphone means includes a microphone in a 2 cubic centimeter coupler for coupling the amplifying device to said microphone.
- said amplifying devices are hearing aids having microphones amplifiers and receivers with said receivers coupled to said microphone means for transmitting sound picked up and amplified by said hearing rectifying 9.
- said analog to digital conversion means includes a rectifying means for rectifying said signals from said microphone means and a logarithmic amplifier for converting linear signals from said rectifying means to logarithmic signals whereby the output of said analog to digital conversion means will be in decibels.
Abstract
A digital display hearing aid gain analyzer is provided for measuring the gain of hearing aids over a predetermined frequency range. A sine wave oscillator generates a predetermined sine wave frequency in an anechoic chamber. The hearing aid to be tested is then connected in the chamber to a microphone pickup housed in a 2 cubic centimeter coupler and picks up and amplifies the sine wave signal in the chamber which is then converted from a linear sine wave signal to a logarithmic signal to a digital type signal indicative of the gain of the hearing aid which is then displayed on Nixie tubes.
Description
United States Patent Lamp 1 Sept. 19, 1972 [541 DIGITAL'HEARING AID GAIN ANALYZER [72] Inventor:
Assignee:
Filed:
Appl. No.:
Oct. 28, 1970 Paul F. Lamp, Casselberry, Fla.
E1ectone,lnc., Orange County, Fla.
US. Cl. ..l79/l75.1 A, 179/107 R Int. Cl. ..H04r 29/00 Field of Search.....l79/l75.l A, 175.1 R, 107 R,
179/1 N, 1 MN; 181/O.5 AP
References Cited UNITED STATES PATENTS Barney et a1 ..l81/0.5 AP
FOREIGN PATENTS OR APPLICATIONS Primary Examiner- Kathleen H. Claffy Assistant Examiner-Douglas W. Olms Attorney-Duckworth & Hobby [5 7] ABSTRACT Germany ..179/175.l A
DIGITAL HEARING AID GAIN ANALYZER BACKGROUND OF THE INVENTION The present invention relates to gain analyzers and especially to gain analyzers for analyzing the gain of hearing aids displaying the gain in digital form.
In the past it has been common to provide various types of gain analyzers for different types of amplifiers. This has been especially true in audio amplifiers in which the gain is measured as the ratio of the output voltage to the input voltage. These circuits generally relate to the input and output voltages, and are measured by isolating the circuit from the remaining circuit and providing means for measuring the input and output voltages and comparing these voltages. However, these types of gain analyzers have not been satisfactory for hearing aid testing in that they require that the hearing aid be dismantled and a predetennined voltage applied to the amplifier section and measured at the output, which voltage must be measured across various ranges of frequencies. The hearing aid microphone and receiver of the hearing aid must be tested separately.
Accordingly, it is one object of the present invention to provide a gain analyzer for hearing aids in which the hearing aid can be easily attached without disassemble and the gain rapidly measured and displayed in digital form across a range of stepped frequencies to determine how well the hearing aid is operating and whether it requires repair or replacement.
SUMMARY OF THE INVENTION The present invention relates to a gain analyzer for hearing aids, or the like, having a digital display. A sine wave generator or oscillator is provided which can generate a sine wave over a wide range of frequencies in predetermined steps which waves are converted to sound by a transducer located in an anechoic chamber. The hearing aid to be tested is placed in a chamber with its receiver end connected to a microphone pickup in a 2 cubic centimeter coupler which coupler simulates the cavity of a human ear and isolates the microphone from the chamber. With the hearing aid turned on the microphone will pick up signals generated by a sine wave oscillator. Analog-to-digital conversion circuitry converts the signals from the hearing aid to digital signals indicative of the gain of the hearing aid. The digital signals are counted and displayed on Nixie tubes in digital form.
BRIEF DESCRIPTION OF THE DRAWINGS Other objects, features and advantages of this invention will be apparent from a study of the written description and the drawings, in which FIG. 1 is a perspective of a gain analyzer illustrating the inputs and digital displays; and
FIG. 2 is a block diagram of one embodiment of the electrical components of the present invention.
DESCRIPTION OF THE PREFERRED EMBODIMENTS Referring now to FIG. 1 a gain analyzer is illustrated in a casing l 1 and having a control panel 12 with an onoff switch 13 and a light 14 to indicate when the apparatus is in an operative position. Push-switches l allow the selection of any one of a plurality of frequencies, in this case starting with 250 through 4,000, having steps of 500, 1,000, 1,500, 2,000 and 3,000. The control panel also has a digital display output 16 which displays the gain of an amplifier in decibels in digital form for easy reading and has a reset switch 17 and a count switch 18. A liftable top 20 allows a hearing aid to be inserted inside an anechoic chamber for testing.
Referring now to FIG. 2 each of the switches 15 controls the sine wave oscillator 21 to generate a predetermined sine wave frequency which is applied to a calibration 22. The calibration board consists of a series of parallel connected adjustable resistors or rheostats each in series with a switch so that each one can be switched and adjusted to assure the correct output level for that frequency. TI-Ie signal is next applied to a speaker amplifier 23 where the signal is amplified which amplifier is coupled to a speaker 24 through a coupling capacitor 25. Speaker transducer 24 is located in an anechoic chamber 26 and reproduces the sine wave at a predetermined frequency and gain in the chamber 26. The chamber 16 may have a hearing aid 27 placed therein with its receiving tube 28 connected to a microphone or similar transducer 30. Thus with the hearing aid turned to an on position, the sine wave oscillator operated at a predetermined frequency, the hearing aid will pick up the sound generated in the chamber 26, amplify it, and produce the amplified sound in the sound tube 28 which is picked up by the microphone 30 housed inside a commercially available 2 cubic centimeter coupler which simulates the human ear and also isolates the microphone 30 from the chamber 26. Microphone 30 impinges the signal upon a microphone amplifier 31 which amplifies the signal and couples it through a capacitor 32 ro a precision AC rectifier 33. The AC rectifier 33 converts the alternating current signal to direct current which direct current may be intermittent in nature. The AC rectifier 33 applies the signal to a DC logarithmic amplifier 34, which amplifier provides an amplified output which is a logarithmic function for conversion of linear-to-log, hence decibels, of the input, which signal is then applied to an offset amplifier 35 and then to a wide band voltage controlled oscillator-36. The voltage controlled oscillator is one in which the oscillator frequency varies in proportion to the controlled voltage being applied to the oscillator. These signals are then applied to a Schmitt trigger 37 which gives fixed output levels for predetermined input levels. The output of the Schmitt trigger is applied to the first decade counter 38 which provides one pulse output for each pulse applied to the input decade counter. The output of the decade counter is applied to inverter 40 into a second decade counter 41. Inverter 40 inverts the signal from a decade counter for the decoder driver 42 which drives a units Nixie tube 43 for displaying the units portion of the output in decibels. Second decade counter 41 receives only one input pulse for every 10 input pulses to decade counter 38 and therefore counts in tens. The output from the decade counter 41 is applied to a second inverter 44 for inverting the signal and applying to the decoder driver 45 for providing the output for the display Nixie tubes 46 which is a tens unit. A reset switch 27 discharges the decade counter for resetting the display tubes for the next frequency test. A counting switch 48 is connected to a one-shot or monostable multivibrator 50 which is activated by the count switch 48 and will actuate the monostable multivibrator 50 for gating counting signals to the decade counter 41. The monostable or one-shot multivibrator 50 has only one condition of steady state equilibrium in which the circuit can remain for an indefinite period of time and there is one condition of momentary equilibrium in which the circuit remains on for one millisecond period of time. Each time the triggering pulse from the count switch 48 is applied the circuit first switches to the momentary equilibrium condition and then after a finite period of time reverses to the original condition and remains in that condition until another pulse is applied. Thus, by pushing the count switch 48 a gate is opened for l millisecond by the monostable to allow counting of pulses from the voltage controlled oscillator to the decade counter. Although the voltage controlled oscillator runs at a 5 digit frequency, the l millisecond gate allows only the first two digits to be counted, hence increasing the count accuracy 1,000: 1.
Thus it should be clear at this point that a digital hearing aid gain analyzer has been provided which will accept a head worn type hearing aid and measure its gain displaying it in decibels by virtue of Nixie display tubes. The power supply for the electronic circuits is not illustrated since it is of course assumed that power supply will be required which may include simple half wave and full wave bridge rectifiers to provide the desired voltages. The analog circuitry may comprise the sine wave oscillator 15, a voltage control oscillator 36, a microphone amplifier 31, a precision rectifier 33 and direct current logarithmic amplifier 34 and an offset amplifier 35. Sine oscillator is a Wien bridge type which produces a pure sine wave to drive a speaker 24 with pure tone. This tone in turn is sensed by the hearing aid 27 to be measured; the gain of the hearing aid is in turn sensed through a microphone 30 and amplified by the microphone amplifier 31. This amplified signal is rectified by the precision rectifier circuit 33. The output of this rectifier 33, which is a varying minus DC voltage, drives a DC logarithmic amplifier 34 converting a linear voltage into a logarithmic one, hence converting it to decibels. DC log amplifier 34 drives the offset amplifier 35 which in turn supplies the voltage controlled oscillator with a voltage comparable to the gain of the hearing aid 27. The voltage controlled oscillator 36 is a wide-band complimentary type flip-flop driven by a current source. Its frequency will vary depending upon the gain of the hearing aid. It is this frequency that is fed to the digital counter which in turn displays it as decibel gain. The digital displaying counter circuitry enhances a units and tens counter of the binary type. Units to be counted are produced by a voltage control oscillator 37, shaped through a Schmitt trigger 37 and fed into the unit counter 38. The counting time is determined by one-shot multi-vibrator 30 which may be set to a l millisecond time period. Since this is a manual type counter, the reset switch 48 must be operated before the count switch will allow the counter to count. The individual circuits used in the present invention are of conventional design and other circuits of the same general type can be utilized as desired. Accordingly this invention is not to be construed as limited to the particular forms disclosed herein since these are to be regarded as illustrative rather than restrictive.
I claim:
1. A gain analyzer apparatus for measuring the gain of audio amplifying devices comprising in combination:
a. chamber means;
b. signal generating means for generating predetermined audio frequencies;
c. transducer means coupled to said signal generating means and located in said chamber means for producing said audio frequencies in said chamber means;
(1. microphone means located in said chamber means and having means for acoustically coupling the output of an audio amplifying device thereto, whereby said audio amplifying device is adapted to amplifying said audio frequencies in said chamber means and apply said amplified audio frequencies to said microphone means;
e. analog to digital conversion means coupled to said microphone means for generating digital signals from the output from said microphone means, said digital signals being indicative of the gain of the amplifying device being analyzed; and
f. counting means coupled to said analog to digital conversion means for counting digital signals received from said analog to digital conversion means.
2. The apparatus according to claim 1 in which said chamber means is an anechoic chamber.
3. The apparatus according to claim 1 in which said counting means includes Nixie display tubes for'displaying the counted digital signals as the gain of said amplifying device at a predetermined input frequency.
4. The apparatus according to claim 3 in which said transducer means is a speaker.
5. The apparatus according to claim 4 in which said microphone means includes a microphone in a 2 cubic centimeter coupler for coupling the amplifying device to said microphone.
6. The apparatus according to claim 5, in which said microphone is located in a coupler having a simulated human ear cavity.
7. The apparatus according to claim 6 in which said signal generating means is a sine wave oscillator.
8. The apparatus according to claim 7 in which said amplifying devices are hearing aids having microphones amplifiers and receivers with said receivers coupled to said microphone means for transmitting sound picked up and amplified by said hearing rectifying 9. The apparatus according to claim 1 in which said analog to digital conversion means includes a rectifying means for rectifying said signals from said microphone means and a logarithmic amplifier for converting linear signals from said rectifying means to logarithmic signals whereby the output of said analog to digital conversion means will be in decibels.
Claims (9)
1. A gain analyzer apparatus for measuring the gain of audio amplifying devices comprising in combination: a. chamber means; b. signal generating means for generating predetermined audio frequencies; c. transducer means coupled to said signal generating means and located in said chamber means for producing said audio frequencies in said chamber means; d. microphone means located in said chamber means and having means for acoustically coupling the output of an audio amplifying device thereto, whereby said audio amplifying device is adapted to amplifying said audio frequencies in said chamber means and apply said amplified audio frequencies to said micropHone means; e. analog to digital conversion means coupled to said microphone means for generating digital signals from the output from said microphone means, said digital signals being indicative of the gain of the amplifying device being analyzed; and f. counting means coupled to said analog to digital conversion means for counting digital signals received from said analog to digital conversion means.
2. The apparatus according to claim 1 in which said chamber means is an anechoic chamber.
3. The apparatus according to claim 1 in which said counting means includes Nixie display tubes for displaying the counted digital signals as the gain of said amplifying device at a predetermined input frequency.
4. The apparatus according to claim 3 in which said transducer means is a speaker.
5. The apparatus according to claim 4 in which said microphone means includes a microphone in a 2 cubic centimeter coupler for coupling the amplifying device to said microphone.
6. The apparatus according to claim 5, in which said microphone is located in a coupler having a simulated human ear cavity.
7. The apparatus according to claim 6 in which said signal generating means is a sine wave oscillator.
8. The apparatus according to claim 7 in which said amplifying devices are hearing aids having microphones amplifiers and receivers with said receivers coupled to said microphone means for transmitting sound picked up and amplified by said hearing rectifying
9. The apparatus according to claim 1 in which said analog to digital conversion means includes a rectifying means for rectifying said signals from said microphone means and a logarithmic amplifier for converting linear signals from said rectifying means to logarithmic signals whereby the output of said analog to digital conversion means will be in decibels.
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US8482370A | 1970-10-28 | 1970-10-28 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| US3692959A true US3692959A (en) | 1972-09-19 |
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| US84823A Expired - Lifetime US3692959A (en) | 1970-10-28 | 1970-10-28 | Digital hearing aid gain analyzer |
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| US (1) | US3692959A (en) |
Cited By (25)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE2461070A1 (en) * | 1974-01-03 | 1975-07-10 | George J Frye | ACOUSTIC TESTING SYSTEM |
| US3912880A (en) * | 1973-07-06 | 1975-10-14 | Edwin John Powter | Acoustic measurement |
| US3979567A (en) * | 1975-02-18 | 1976-09-07 | Frye G J | Microphone coupler for hearing aid having inverted conical end configuration |
| US4065647A (en) * | 1974-01-03 | 1977-12-27 | Frye G J | Automatic acoustical testing system |
| US4095057A (en) * | 1976-03-19 | 1978-06-13 | National Research Development Corporation | Frequency response testing apparatus |
| US4191864A (en) * | 1978-08-25 | 1980-03-04 | American Hospital Supply Corporation | Method and apparatus for measuring attack and release times of hearing aids |
| US4357499A (en) * | 1979-03-22 | 1982-11-02 | Brueel Per V | Acoustic test box |
| US4805728A (en) * | 1987-09-29 | 1989-02-21 | Robert Carter | Sound system with anechoic enclosure |
| US5995036A (en) * | 1998-03-17 | 1999-11-30 | Sonic Innovations, Inc. | Passive switched capacitor delta analog-to-digital converter with programmable gain control |
| US6313773B1 (en) | 2000-01-26 | 2001-11-06 | Sonic Innovations, Inc. | Multiplierless interpolator for a delta-sigma digital to analog converter |
| US6408318B1 (en) | 1999-04-05 | 2002-06-18 | Xiaoling Fang | Multiple stage decimation filter |
| US6757395B1 (en) | 2000-01-12 | 2004-06-29 | Sonic Innovations, Inc. | Noise reduction apparatus and method |
| US20050008177A1 (en) * | 2003-07-11 | 2005-01-13 | Ibrahim Ibrahim | Audio path diagnostics |
| US20050085343A1 (en) * | 2003-06-24 | 2005-04-21 | Mark Burrows | Method and system for rehabilitating a medical condition across multiple dimensions |
| US20050090372A1 (en) * | 2003-06-24 | 2005-04-28 | Mark Burrows | Method and system for using a database containing rehabilitation plans indexed across multiple dimensions |
| US20070276285A1 (en) * | 2003-06-24 | 2007-11-29 | Mark Burrows | System and Method for Customized Training to Understand Human Speech Correctly with a Hearing Aid Device |
| US20080041656A1 (en) * | 2004-06-15 | 2008-02-21 | Johnson & Johnson Consumer Companies Inc, | Low-Cost, Programmable, Time-Limited Hearing Health aid Apparatus, Method of Use, and System for Programming Same |
| US20080056518A1 (en) * | 2004-06-14 | 2008-03-06 | Mark Burrows | System for and Method of Optimizing an Individual's Hearing Aid |
| US20080167575A1 (en) * | 2004-06-14 | 2008-07-10 | Johnson & Johnson Consumer Companies, Inc. | Audiologist Equipment Interface User Database For Providing Aural Rehabilitation Of Hearing Loss Across Multiple Dimensions Of Hearing |
| US20080165978A1 (en) * | 2004-06-14 | 2008-07-10 | Johnson & Johnson Consumer Companies, Inc. | Hearing Device Sound Simulation System and Method of Using the System |
| US20080187145A1 (en) * | 2004-06-14 | 2008-08-07 | Johnson & Johnson Consumer Companies, Inc. | System For and Method of Increasing Convenience to Users to Drive the Purchase Process For Hearing Health That Results in Purchase of a Hearing Aid |
| US20080240452A1 (en) * | 2004-06-14 | 2008-10-02 | Mark Burrows | At-Home Hearing Aid Tester and Method of Operating Same |
| US20080269636A1 (en) * | 2004-06-14 | 2008-10-30 | Johnson & Johnson Consumer Companies, Inc. | System for and Method of Conveniently and Automatically Testing the Hearing of a Person |
| US20080298614A1 (en) * | 2004-06-14 | 2008-12-04 | Johnson & Johnson Consumer Companies, Inc. | System for and Method of Offering an Optimized Sound Service to Individuals within a Place of Business |
| US10408671B2 (en) * | 2015-04-28 | 2019-09-10 | Verily Life Sciences Llc | Integrated wearable noise dosimeter |
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| DE909969C (en) * | 1942-05-05 | 1954-04-26 | Siemens Ag | Arrangement with beat buzzer |
| US2571979A (en) * | 1946-04-19 | 1951-10-16 | Conn Ltd C G | Acoustic measuring apparatus |
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Cited By (30)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3912880A (en) * | 1973-07-06 | 1975-10-14 | Edwin John Powter | Acoustic measurement |
| DE2461070A1 (en) * | 1974-01-03 | 1975-07-10 | George J Frye | ACOUSTIC TESTING SYSTEM |
| US3922506A (en) * | 1974-01-03 | 1975-11-25 | Frye G J | Acoustical testing system |
| US4065647A (en) * | 1974-01-03 | 1977-12-27 | Frye G J | Automatic acoustical testing system |
| US3979567A (en) * | 1975-02-18 | 1976-09-07 | Frye G J | Microphone coupler for hearing aid having inverted conical end configuration |
| US4095057A (en) * | 1976-03-19 | 1978-06-13 | National Research Development Corporation | Frequency response testing apparatus |
| US4191864A (en) * | 1978-08-25 | 1980-03-04 | American Hospital Supply Corporation | Method and apparatus for measuring attack and release times of hearing aids |
| WO1980000519A1 (en) * | 1978-08-25 | 1980-03-20 | American Hospital Supply Corp | Method and apparatus for measuring attack and release times of hearing aids |
| US4357499A (en) * | 1979-03-22 | 1982-11-02 | Brueel Per V | Acoustic test box |
| WO1983000792A1 (en) * | 1979-03-22 | 1983-03-03 | BRÜEL, Per, Vilhelm | Container for acoustic testing |
| US4805728A (en) * | 1987-09-29 | 1989-02-21 | Robert Carter | Sound system with anechoic enclosure |
| US5995036A (en) * | 1998-03-17 | 1999-11-30 | Sonic Innovations, Inc. | Passive switched capacitor delta analog-to-digital converter with programmable gain control |
| US6408318B1 (en) | 1999-04-05 | 2002-06-18 | Xiaoling Fang | Multiple stage decimation filter |
| US6757395B1 (en) | 2000-01-12 | 2004-06-29 | Sonic Innovations, Inc. | Noise reduction apparatus and method |
| US6313773B1 (en) | 2000-01-26 | 2001-11-06 | Sonic Innovations, Inc. | Multiplierless interpolator for a delta-sigma digital to analog converter |
| US20050085343A1 (en) * | 2003-06-24 | 2005-04-21 | Mark Burrows | Method and system for rehabilitating a medical condition across multiple dimensions |
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