OPTICAL ELECTRO-MECHANICAL HEARING DEVICES WITH SEPARATE POWER AND SIGNAL COMPONENTS

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention is related to hearing systems, devices and methods. Although specific reference is made to hearing aid systems, embodiments of the present invention can be used in many applications where tissue is stimulated with at least one of vibration or an electrical current, for example with wireless communication, the treatment of neurological disorders such as Parkinson's, and cochlear implants.

People like to hear. Hearing devices can be used with communication systems and aids to help the hearing impaired. Hearing impaired subjects need hearing aids to verbally communicate with those around them. Open canal hearing aids have proven to be successful in the marketplace because of increased comfort and an improved cosmetic appearance. Another reason why open canal hearing aides can be popular is reduced occlusion of the ear canal. Occlusion can result in an unnatural, tunnel-like hearing effect which can be caused by large hearing aids which block the ear canal. However, a problem that may occur with open canal hearing aids is feedback. The feedback may result from placement of the microphone in too close proximity with the speaker or the amplified sound being too great. Thus, feedback can limit the degree of sound amplification that a hearing aid can provide. In some instances, feedback may be minimized by using non-acoustic means of stimulating the natural hearing transduction pathway, for example stimulating the tympanic membrane and/or bones of the ossicular chain. A permanent magnet or plurality of magnets may be coupled to the eardrum or the ossicles in the middle ear to stimulate the hearing pathway. These permanent magnets can be magnetically driven to cause motion in the hearing transduction pathway thereby causing neural impulses leading to the sensation of hearing. A permanent magnet may be coupled to the eardrum through the use of a fluid and surface tension, for example as described in U.S. Pat. Nos. 5,259,032 and 6,084,975.

However, work in relation to embodiments of the present invention suggests that magnetically driving the hearing transduction pathway may have limitations. The strength of the magnetic field generated to drive the attached magnet may decrease rapidly with the distance from the field generator coil to the permanent magnet. For magnets implanted to the ossicle, invasive surgery may be needed. Coupling a magnet to the eardrum may avoid the need for invasive surgery. However, there can be a need to align the driver coil with the permanent magnet, and placement of the driver coil near the magnet can cause discomfort for the user, in at least some instances.

An alternative approach is a photo-mechanical system, for example, a hearing device may use light as a medium to transmit sound signals. Such systems are described in U.S. Pat. No. 7,289,639 and U.S. Pat. App. No. U.S. Publication Nos. 2006/0189841. The optical output signal can be delivered to an output transducer coupled to the eardrum or the ossicle. Although optical systems may result in improved comfort for the patient, work in relation to embodiments of the present invention suggests that such systems may result in at least some distortion of the signal such that in some instances the sound perceived by the patient may be less than ideal in at least some instances.

Although pulse width modulation can be used to transmit an audio signal with an optical signal, work in relation to embodiments of the present invention suggests that at least some of the known pulse width modulation schemes may not work well with prior hearing devices in at least some instances. A digital signal output can be represented by a train of digital pulses. The pulses can have a duty cycle (the ratio of time in active to the overall period) that varies with the intended analog amplitude level. The pulses can be integrated to find the intended audio signal, which has an amplitude equal to the duty cycle multiplied by the pulse amplitude. When the amplitude of the intended audio signal decreases, the duty cycle can be decreased so that the amplitude of the integrated audio signal drops proportionally. Conversely, when the amplitude of the intended audio signal increases, the duty cycle can be increased so that the amplitude rises proportionally. Analog audio signals may vary positively or negatively from zero. At least some known pulse width modulation schemes may use a quiescent level, or zero audio level, represented by a 50% duty cycle. Decreases in duty cycle from this quiescent level can correspond to negative audio signal amplitude while increases in duty cycle can correspond to positive audio signal amplitude. Because this quiescent level is maintained, significant amounts of power may be consumed in at least some instances. While this amount of power use may not be a problem for larger signal transduction systems, in at least some instances this power use can pose problems for hearing devices, which are preferably small and may use small batteries that are ideally infrequently replaced.

For the above reasons, it would be desirable to provide hearing systems which at least decrease, or even avoid, at least some of the above mentioned limitations of the current hearing devices. For example, there is a need to provide a comfortable hearing device with less distortion and less feedback than current devices.

2. Description of the Background Art

Patents of interest include: U.S. Pat. Nos. 3,585,416, 3,764,748, 5,142,186, 5,554,096, 5,624,376, 5,795,287, 5,800,336, 5,825,122, 5,857,958, 5,859,916, 5,888,187, 5,897,486, 5,913,815, 5,949,895, 6,093,144, 6,139,488, 6,174,278, 6,190,305, 6,208,445, 6,217,508, 6,222,302, 6,422,991, 6,475,134, 6,519,376, 6,626,822, 6,676,592, 6,728,024, 6,735,318, 6,900,926, 6,920,340, 7,072,475, 7,095,981, 7,239,069, 7,289,639, D512,979, and EP1845919. Patent publications of interest include: PCT Publication Nos. WO 03/063542, WO 2006/075175, U.S. Publication Nos. 2002/0086715, 2003/0142841, 2004/0234092, 2006/0107744, 2006/0233398, 2006/075175, 2008/0021518, and 2008/01079292. Commonly owned U.S. Pat. No. 5,259,032 (Attorney Docket No. 026166-000500US), U.S. Pat. No. 5,276,910 (Attorney Docket No. 026166-000600US), U.S. Pat. No. 5,425,104 (Attorney Docket No. 026166-000700US), U.S. Pat. No. 5,804,109 (Attorney Docket No. 026166-000200US), U.S. Pat. No. 6,084,975 (Attorney Docket No. 026166-000300US), U.S. Pat. No. 6,554,761 (Attorney Docket No. 026166-001700US), U.S. Pat. No. 6,629,922 (Attorney Docket No. 026166-001600US), U.S. Publication Nos. 2006/0023908 (Attorney Docket No. 026166-000100US), 2006/0189841 (Attorney Docket No. 026166-000820US), 2006/0251278 (Attorney Docket No. 026166-000900US), and 2007/0100197 (Attorney Docket No. 026166-001100US), the complete disclosures of which herein are incorporated herein by reference and suitable for combination in accordance with some embodiments of the present invention, may also be of interest. Journal publications of potential interest include: Ayatollahi et al., “Design and Modeling of Micromachines Condenser MEMS Loudspeaker using Permanent Magnet Neodymium-Iron-Boron (Nd—Fe—B)”, ISCE, Kuala Lampur, 2006; Birch et al, “Microengineered Systems for the Hearing Impaired”, IEE, London, 1996; Cheng et al., “A silicon microspeaker for hearing instruments”, J. Micromech. Microeng., 14(2004) 859-866; Yi et al., “Piezoelectric microspeaker with compressive nitride diaphragm”, IEEE, 2006, and Zhigang Wang et al., “Preliminary Assessment of Remote Photoelectric Excitation of an Actuator for a Hearing Implant”, IEEE Engineering in Medicine and Biology 27th Annual Conference, Shanghai, China, Sep. 1-4, 2005 Other publications of interest include: Gennum GA3280 Preliminary Data Sheet, “Voyager TD™. Open Platform DSP System for Ultra Low Power Audio Processing” and National Semiconductor LM4673 Data Sheet, “LM4673 Filterless, 2.65W, Mono, Class D audio Power Amplifier”; and Lee et al., “The Optimal Magnetic Force For A Novel Actuator Coupled to the Tympanic Membrane: A Finite Element Analysis,” Biomedical Engineering: Applications, Basis and Communications, Vol. 19, No. 3 (171-177), 2007.

BRIEF SUMMARY OF THE INVENTION

The present invention is related to hearing systems, devices and methods. Embodiments of the present invention can provide improved audio signal transmission which overcomes at least some of the aforementioned limitations of current systems. The systems, devices, and methods described herein may find application for hearing devices, for example open ear canal hearing aides. A transducer can be supported with and configured to vibrate at least one of an eardrum, an ossicle or a cochlea. Active circuitry powered with an optical signal can be used to drive the transducer in response to the optical signal so as to provide the user with high quality sound. Therefore, the user can have the beneficial comfort of optical coupling and the high quality sound of active circuitry.

In a first aspect, embodiments of the present invention provide a device to transmit an audio signal. At least one light source is configured to transmit the audio signal with at least one wavelength of light. At least one detector is configured to detect the audio signal and generate at least one electrical signal in response to the at least one wavelength of light. A transducer is supported with and configured to vibrate at least one of an eardrum, an ossicle or a cochlea. Active circuitry is coupled to at least one detector and the transducer to drive the transducer in response to the electrical signal.

In many embodiments, a power storage device is coupled to the at least one detector and the active circuitry to power the active circuitry with energy from the at least one detector. The power storage device and the active circuitry can be configured with size and mass for support with at least one of the eardrum, the ossicle or the cochlea. The at least one light source and the at least one detector can be configured to supply power to the power storage device and the active circuitry so as to drive the transducer with energy from the at least one light source. The power storage device may comprise at least one of a capacitor or a miniature rechargeable battery.

In many embodiments, the photodetector comprises at least one of as crystalline silicon, amorphous silicon, micromorphous silicon, black silicon, cadmium telluride, copper indium, gallium selenide, or indium gallium arsenide.

In many embodiments, the transducer comprises at least one of a piezo electric transducer, a flex tensional transducer, a wire coil, a magnet or an acoustic speaker. The active circuitry may comprise at least one of a transistor, an amplifier, a logic gate or a flip flop.

In many embodiments, the audio signal transmitted from the at least one light source to the at least one detector comprises a pulse width modulated signal. The pulse width modulated (hereinafter “PWM”) signal may comprise at least one of a delta PWM signal, a differential drive PWM signal, a delta-sigma PWM signal or a differential delta-sigma PWM signal.

Many embodiments further comprise circuitry coupled to an input configured to receive the audio signal. The circuitry is coupled to the at least one light source, and the circuitry is configured to adjust an output of the at least one light source to power the active circuitry in response to the audio signal. The circuitry can be configured measure the audio signal to determine energy of the audio signal and to adjust an amount of energy transmitted with the at least one light source in response to the power of the audio signal. For example, the circuitry can be configured to adjust at least one of a DC bias or an amplitude of pulses of the at least one light source in response to the audio signal to power the active circuitry. Alternatively or in combination, the at least one light source may comprise a first light source configured to transmit the audio signal and a second light source configured to transmit power, and the circuitry is configured to adjust and amount of power transmitted with the second light source in response to the audio signal.

In many embodiments, the circuitry comprises a sound processor configured to measure the audio signal and to adjust the output of the at least one light source to power the active circuitry in response to the audio signal.

In another aspect, embodiments of the present invention provide a system to transmit an audio signal. An input transducer assembly comprises at least one light source configured to emit at least one wavelength of light. An output transducer assembly comprises at least one detector configured to detect the at least one wavelength of light, active circuitry coupled to the at least one detector and a transducer electrically coupled to the active circuitry. The transducer is configured to vibrate at least one of an eardrum, an ossicle, or a cochlea of the user in response to the at least one wavelength of light.

In many embodiments, the output transducer assembly is supported with the at least one of the eardrum, the ossicle or the cochlea. The output transducer assembly may comprise a power storage device supported with the at least one of the eardrum, the ossicle. The power storage device can be configured with at least one of a size or a mass to vibrate with the at least one of the eardrum, the ossicle or the cochlea. The active circuitry can be coupled to the detector and the transducer to drive the transducer in response to the at least one wavelength of light. The active circuitry can be configured with at least one of a size or a mass to vibrate with the at least one of the eardrum, the ossicle or the cochlea.

In many embodiments, the input transducer is configured to transmit the at least one wavelength of light as a pulse width modulated signal and wherein the output transducer assembly is configured to vibrate the at least one of the eardrum, the ossicle or the cochlea in response to the pulse width modulated signal.

In many embodiments, the at least one wavelength of light comprises a first wavelength of light and a second wavelength of light, and the at least one light source comprises a first light source configured to emit the first wavelength and a second light source configured to emit the second wavelength of light. The at least one detector comprises a first detector configured to move the transducer with a first movement in response to a first at least one wavelength of light. A second detector is configured to move the transducer with a second movement in response to the second at least one wavelength, in which the second movement is opposite the first movement.

The at least one wavelength of light comprises at least one of an ultraviolet light, a visible light or an infrared light.

In another aspect, embodiments of the present invention provide a method of transmitting an audio signal. At least one wavelength of light is emitted from at least one light source. The at least one wavelength of light is detected to generate and electrical signal. At least one of an eardrum, an ossicle, or a cochlea of a user is vibrated in response to the electrical signal.

In many embodiments, the output transducer assembly is supported with the at least one of the eardrum, the ossicle or the cochlea. The output transducer assembly may comprise a power storage device supported with the at least one of the eardrum, the ossicle or the cochlea. The power storage device may vibrate when the at least one of the eardrum, the ossicle or the cochlea is vibrated. The output transducer assembly may comprise active circuitry supported with the at least one of the eardrum, the ossicle or the cochlea. The active circuitry can be coupled to the detector and the transducer to drive the transducer in response to the at least one wavelength of light. The active circuitry may vibrate when the at least one of the eardrum, the ossicle or the cochlea vibrates.

In another aspect, embodiments of the present invention provide device to stimulate a target tissue. The device comprises at least one light source configured to transmit a pulse width modulated light signal with at least one wavelength of light. At least one detector is coupled to the target tissue to stimulate the target tissue in response to the modulated light signal.

In many embodiments, an implantable detector is configured to stimulate the tissue with at least one of a vibration or a current and wherein the detector is coupled to at least one of a transducer or at least two electrodes. For example, the detector can be configured to stimulate the tissue with the current, and the detector can be coupled to the at least two electrodes. The target tissue may comprise a cochlea of the user, and the modulated light signal may comprise an audio signal.

In another aspect, embodiments of the present invention provide a method of stimulating a target tissue. A pulse width modulated light signal comprising at least one wavelength of light is emitted from at least one light source. The target tissue is stimulated in response to the modulated light signal.

In many embodiments, the target tissue is stimulated with at least one of a vibration or a current. The target tissue can be stimulated with the current, and the implantable detector can be coupled to at least two electrodes and stimulate the tissue in response to the modulated signal comprising the at least one wavelength of light. The target tissue may comprise a cochlea of the user and the modulated light signal may comprise an audio signal.

In another aspect, embodiments of the present invention provide device to transmit an audio signal comprising sound to a user. The device comprises means for transmitting the audio signal and means for detecting the audio signal such that the user hears the sound

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows a hearing system using photo-electro-mechanical sound transduction, according to embodiments of the present invention;

FIG. 2 is a graphical representation of components of the hearing system as in FIG. 1;

FIG. 2A shows an ear canal module comprising the components of FIG. 2, according to embodiments of the present invention;

FIG. 3 shows a photo-electro-mechanical transducer assembly for use with the system as in FIGS. 1 and 2;

FIG. 3A shows an implantable output assembly for use with components of a system as in FIGS. 1 and 2;

FIG. 4A shows a first rotational movement comprising first rotation with a flex tensional transducer and a second rotation movement comprising a second rotation opposite the first rotation, according to embodiments of the present invention;

FIG. 4B shows a translational movement in a first direction with a coil and magnet and a second translational movement in a second direction opposite the first direction; according to embodiments of the present invention.

FIG. 5 shows the circuitry of a hearing system, as in FIGS. 1 and 2;

FIG. 6 shows a pulse width modulated signal suitable for use with the transducer assembly;

FIG. 7 shows a pair of complementary digital signals, according to embodiments of the present invention;

FIG. 8 shows a digital signal, according to embodiments of the present invention;

FIG. 9 shows circuitry for use with the signal shown by FIG. 8;

FIG. 10 shows the circuitry of an output transducer assembly for a hearing system, as in FIGS. 1 and 2;

FIG. 10A shows PWM pulses biased in response to energy of the audio signal, according to embodiments of the present invention;

FIG. 10B shows PWM pulses with amplitudes adjusted in response to energy of the audio signal, according to embodiments of the present invention;

FIG. 10C shows voltage to a second light source configured to transmit power in response to energy of the audio signal, according to embodiments of the present invention; and

FIG. 11 shows a method of transmitting sound to a user, according to embodiments of the present invention.

DETAILED DESCRIPTION OF THE INVENTION

Embodiments of the present invention can be used in many applications where tissue is stimulated with at least one of vibration or an electrical current, for example with wireless communication, the treatment of neurological disorders such as Parkinson's, and cochlear implants. An optical signal can be transmitted to a photodetector coupled to tissue so as to stimulate tissue. The tissue can be stimulated with at least one of a vibration or an electrical current. For example, tissue can be vibrated such that the user perceives sound. Alternatively or in combination, the tissue such as neural tissue can be stimulated with an electrical current such that the user perceives sound. The optical signal transmission architecture described herein can have many uses outside the field of hearing and hearing loss and can be used to treat, for example, neurological disorders such as Parkinson's.

Embodiments of the present invention can provide optically coupled hearing devices with improved audio signal transmission. The systems, devices, and methods described herein may find application for hearing devices, for example open ear canal hearing aides. Although specific reference is made to hearing aid systems, embodiments of the present invention can be used in any application where sound is amplified for a user, for example with wireless communication and for example with surgical implants to the middle ear and cochlear implants.

As used herein active circuitry encompasses circuitry that can amplify an input signal so as to produce an output signal having more power than the input signal. The active circuitry may comprise at least one of a transistor, an amplifier, a logic gate or a flip flop. The additional power of the output signal can be obtained from a power storage device. The power storage device may comprise at least one of a miniature rechargeable battery or a capacitor. In many embodiments, the power storage device is charged and/or recharged with optical power from a light source, such as the light source used to transmit the audio signal. At least one of the active circuitry or the power storage device can be configured to vibrate with the transducer.

A hearing aid system using photo-electro-mechanical transduction is shown in FIG. 1. The hearing system 10 includes an input transducer assembly 20 and an output transducer assembly 30. As shown in FIG. 1, the input transducer assembly 20 is located at least partially behind the pinna P, although the input transducer assembly may be located at many sites such as in pinna P or entirely within ear canal EC, for example, as with microphone 22. The input transducer assembly 20 receives a sound input, for example an audio sound. With hearing aids for hearing impaired individuals, the input is ambient sound. In this case, input transducer assembly can include a suitable amplifier or other electronic interface. In some embodiments, the input may be an electronic sound signal from a sound producing or receiving device, such as a telephone, a cellular telephone, a Bluetooth connection, a radio, a digital audio unit, and the like.

Input transducer assembly 20 includes a light source, such as an LED or a laser diode. The light source produces a modulated light output based on the sound input. The light output comprises at least one wavelength λ of light that is delivered to a target location near or adjacent to output transducer assembly 30 by a light transmission element 12 which traverses ear canal EC. Light transmission element 12 may be an optic fiber or bundle of optic fibers. The light output comprising at least one wavelength λ is selected to couple to the output transducer assembly 30 to provide a signal to output transducer assembly 30 so that it can produce mechanical vibrations. For example, light output comprising at least one wavelength λ may cause output transducer assembly 30 to move in a first direction 40 or in a second direction 45. Second direction 45 may be opposite first direction 40. The at least one wavelength λ may comprise a plurality of wavelengths, for example a first wavelength to move the transducer of the transducer assembly in first direction 40 and a second wavelength to move the transducer of the transducer assembly in second direction 45. When properly coupled to the subject's hearing transduction pathway, the mechanical vibrations induces neural impulses in the subject which are interpreted by the subject as the original sound input, or at least something reasonably representative of the original sound input.

The output transducer assembly 30 can be configured to couple to some point in the hearing transduction pathway of the subject in order to induce neural impulses which are interpreted as sound by the subject. Preferably, the output transducer assembly 30 can couple to the tympanic membrane TM. Alternatively, the output transducer assembly 15 may couple to a bone in the ossicular chain OS or directly to the cochlea CO where it is positioned to vibrate fluid within the cochlea CO. Specific points of attachment, for example to at least one the tympanic membrane, an ossicle of the middle ear or the cochlea, are described in prior U.S. Pat. Nos. 5,259,032; 5,456,654; 6,084,975; and 6,629,922 and 7,289,639.

The input transducer assembly 20 can be configured in many ways to couple to the output transducer assembly 30. For example, the input transducer assembly 20 may comprise a behind the ear unit (hereinafter “BTE”), such that many of the electronic components can be positioned behind the ear with light transmission element 12 extending into the ear canal. Alternatively, the input transducer assembly 20 may comprise a module configured for placement in the ear canal, for example as described in U.S. Pat. No. 7,289,639. The circuitry of the input transducer assembly as described herein can be sized and configured for placement in the ear canal, such that the user hears high quality sound with an input transducer assembly configured for placement in the ear canal.

FIG. 2 graphically depicts components of hearing system 10. The input transducer assembly 20 may comprise an input transducer 210, an audio processor 220, an emitter driver 240 and emitters 250. The output transducer assembly 30 may comprise filters 260, detectors 270, a transducer driver 280 and an output transducer 290. Input transducer 210 takes ambient sound and converts it into an analog electrical signal. Input transducer 210 often includes a microphone which may be placed in the ear canal, behind the ear, in the pinna, or generally in proximity with the ear. Audio processor 220 may provide a frequency dependent gain to the analog electrical signal. The analog electrical signal is converted to a digital electrical signal by digital output 230. Audio processor 220 may comprise many audio processors, for example an audio processor commercially available from Gennum of Corporation of Burlington, Canada and GA3280 hybrid audio processor commercially available from Sound Design Technologies, Ltd. of Burlington Ontario, Canada. Digital output 230 includes a modulator, for example, a pulse-width modulator or a delta-sigma converter. Emitter driver 240 processes the digital electrical signal so that it is specific to optical transmission and the power requirements of emitters 250.

Emitters 250 produce a light output representative of the electrical signal. For a dual component electrical signal, emitters 250 can include two light sources, one for each component, and produce two light output signals 254, 256. The light source may be, for example, an LED or a laser diode, and the light output may be in the infrared, visible, or ultraviolet wavelength. For example, the light source may comprise an LED that emits at least one wavelength of light comprising a central wavelength and a plurality of wavelengths distributed about the central wavelength with a bandwidth of about 40 nm. The light source may comprise a laser diode that emits at least one wavelength of light comprising a central wavelength with a bandwidth no more than about 2 nm, for example no more than 1 nm. The first at least one wavelength from the first source can be different from the second at least one wavelength from the second source, for example different by at least 80 nm, such that the first at least one wavelength can be separated from the second at least one wavelength of light. The first at least one wavelength may comprise a first bandwidth, for example 60 nm, and the second at least one wavelength may comprise a second bandwidth, for example 60 nm, and the first at least one wavelength can be different from the second at least one wavelength by at least the first bandwidth and the second bandwidth, for example 120 nm.

The light output signals travel along a single or multiple optical paths though the ear canal, for example, via an optic fiber or fibers. The light output signals may spatially overlap. The signals are received by an output transducer assembly which can be placed on the ear canal.

The output transducer assembly comprises components to respond to the optical signal so as to vibrate at least one of the eardrum, the ossicles or the cochlea in response to the optical signal. Detectors 270 receive the light output signals. Detectors 270 include at least one photodetector provided for each light output signal. A photodetector may be, for example, a photodiode, a photovoltaic, or the like. Filters 260 are optionally provided along the optical path. Filters 260 separate the light output signals. For example, a first filter may be provided to transmit the wavelength of output 254 while a second filter transmits the wavelength of output 256. Filters may be any one of the thin film, interference, dichroic, or gel types with either band-pass, low-pass, or high-pass characteristics. For example, the band-pass characteristics may be configured to pass the at least one wavelength of the source, for example configured with a 30 nm bandwidth to pass a 10 nm bandwidth source, as described above. The low-pass and high-pass maybe combined to pass only one preferred wavelength using the low-pass filter and the other wavelength using the high-pass filter.

Each of detectors 270 may comprise at least one photovoltaic material such as crystalline silicon, amorphous silicon, micromorphous silicon, black silicon, cadmium telluride, copper indium gallium selenide, and the like. In some embodiments at least one of photodetectors 270 comprises black silicon, for example as described in U.S. Pat. Nos. 7,354,792 and 7,390,689 and available under from SiOnyx, Inc. of Beverly, Mass. The black silicon may comprise shallow junction photonics manufactured with semiconductor process that exploits atomic level alterations that occur in materials irradiated by high intensity lasers, such as a femto-second laser that exposes the target semiconductor to high intensity pulses as short as one billionth of a millionth of a second. Crystalline materials subject to these intense localized energy events may under go a transformative change, such that the atomic structure becomes instantaneously disordered and new compounds are “locked in” as the substrate re-crystallizes. When applied to silicon, the result can be a highly doped, optically opaque, shallow junction interface that is many times more sensitive to light than conventional semiconductor materials.

Transducer driver 280 converts the light output signals back into digital electrical signals which carries audio information. Output transducer 290 converts the electrical signal representative of sound into a mechanical energy which then is transmitted to a patient's hearing transduction pathway, causing the sensation of hearing. The transducer may be a piezoelectric transducer, a flex tensional transducer, a magnet and wire coil, or a microspeaker.

Alternatively to the transducer driver 280, at least two electrodes can be coupled to the at least one of the detectors, such that the user perceives sound in response to tissue stimulation from the at least two electrodes. The at least two electrodes can be configured for placement at least partially in the cochlea of the user, such that the user perceives sound in response to the light output.

Many of he above components can be sized and positioned so as to fit within the BTE unit positioned behind the ear.

FIG. 2A shows components of input transducer assembly 20 positioned in a module sized to fit in the ear canal of the user. The module may comprise an outer housing 246 shaped to the ear of the user, for example with a mold of the ear canal. The module may comprise a channel extending from a proximal end where the input transducer 210 is located to a distal end from which light is emitted, such that occlusion is decreased.

FIG. 3 shows an output transducer assembly 300 placed on the tympanic membrane TM, also referred to as the eardrum. Output transducer assembly 300 comprises circuitry which is used to convert light output signals into electrical energy and mechanical energy. Output transducer assembly 300 includes photodetectors 320, 325. Photodetectors 320, 325 detect light output signals 310, 315, respectively, and convert the light output into electrical signals. Output transducer assembly 300 comprises a power storage component 330. Power storage component 330 may comprise at least one of a capacitor, a miniature rechargeable battery, or known power storage device. The power storage component can provide electrical power for an active circuitry component 340. The active circuitry component may comprise at least one of an amplifier or a flip flop. The active circuitry component 340 is coupled to photodetectors 320, 325 to receive the light output signals 320, 325, respectively. Optical filters, as described above, can be used. The active circuitry component applies electrical energy to the load in response to input signals 320, 325 respectively. The electrical signals reach load 350 which converts the electrical signals into a mechanical output such as a vibration. Load 350 may comprise a load from many known transducers, for example at least one of a piezoelectric transducer, a flex tensional transducer, or a wire coil coupled to an external magnet.

In some embodiments, the output transducer assembly and output circuitry can be positioned on and/or supported with an ossicle, for example as described in U.S. Pat. No. 7,289,639.

FIG. 3A shows an implantable output assembly for use with components of a system as in FIGS. 1 and 2. The implantable output assembly 30 may comprise at least two electrodes 390 and an extension 392 configured to extend to a target tissue, for example the cochlea. The implantable output assembly can be configured for placement in many locations and to stimulate many target tissues, such as neural tissue. The at least two electrodes can be coupled to the circuitry so as to comprise a load in a manner similar to transducer 310 described above. A current I flows between the electrodes in response to the optical signal. For example the implantable output assembly can be configured to extend from the middle ear to the cochlea. The implantable output assembly can be configured in many ways to stimulate a target tissue, for example to treat Parkinson's.

Load 350 may comprise a flex tensional transducer 450. FIG. 4A shows a first rotational movement comprising first rotation 462 with a flex tensional transducer 450 and a second rotation movement comprising a second rotation 464 opposite the first rotation.

In some embodiments, load 350 may comprise a transducer 470 comprising a coil 472 magnetically coupled to a magnet 474. FIG. 4B shows a first translational movement in a first direction 482 and a second translational movement in a second direction 484 opposite the first direction with transducer 470 comprising a coil 472 and magnet 474.

FIG. 5 shows circuitry 500 for use with hearing system 10. Circuitry 500 can be configured to transmit optical power for the output transducer assembly with the optical signal. Circuitry 500 includes an input portion 501 and an output portion 506. Circuitry 500 may use the technique of ratiometric drive, in which two light signals are transmitted, one during “low” signal time, the other during the “high” time of a class A signal.

PWM driver 510 provides a pulse width modulated signal 701, explained more fully below. The pulse width modulated signal from the PWM driver may comprise many known PWM signals, for example at least one of a delta PWM signal, a differential drive PWM signal, a delta-sigma PWM signal or a differential delta-sigma PWM signal.

Logic circuitry can be connected to the output of PWM driver 510. Signal 701 drives light emitter 513 and inverter 519. Inverter 519 produces output signal 512 which drives light emitter 514. Since signal 512 is the inverse of signal 701, light emitter 513 produces light whenever light emitter 514 does not. The light generated by light emitter 513 is conveyed over light channel 520 to light detector 515. The light generated by light emitter 514 is conveyed over light channel 521 to light detector 516. Light detectors 515, 516 are shown connected in series. Light detectors 515, 516 may be photovoltaic cells. Resistors 532, 533 are connected in parallel with detectors 515, 516, respectively, to provide current paths when the output voltage of one detector is lower than the forward diode threshold voltage of the other detector. A power storage device, for example capacitor 547, may also be connected in parallel with detectors 515 and 516 to provide constant voltage power output 545. The power storage device may comprise at least one of a miniature rechargeable battery or a capacitor. Output 545 provides a constant voltage to power active circuit 537, which may comprise an amplifier to drive transducer 538. Light emitter 513 and light emitter 514 are configured to emit light energy so as to power the power storage device and active circuit of output portion 506, such that the output transducer is driven with energy from the light emitter 513 and light emitter 514.

The voltage from the center connection 544 of the two detectors 515, 516 connected in series is connected to drive the input to the active circuit 537. Due to the integrating action of the detectors 515, 516, the voltage from center connection 544 will vary between zero and the maximum voltage in a direct relationship to the ratio of light in channel 520 to the light in channel 521. Optical filters, as described above, can be used. The analog voltage at connection 544 will therefore represent the analog output of PWM converter 510.

Alternatively to connecting the voltage from the active circuit 537 to transducer 538, the active circuit 537 can be coupled to at least two electrodes configured for placement at least partially within the cochlea of the user, such that the user perceives sound in response to electrical stimulation of the cochlea in response to the light output.

FIG. 6 a simple pulse-width modulated signal 601 suitable for use with output transducer assembly. Signal 601, which is digital, can take two levels, a high level or a low level, for example 0 V or 5 V. In some embodiments, signal 601 is always low at the start of time window 603 and transitions to the high level at a variable time 605 within window 603. At the end of window 603, signal 601 returns to the low level. The integrated output can be obtained by multiplying the pulse level output by the ratio of time in the high level to the window 603 time.

Analog signals can often take values above and below zero, and the zero output condition of the modulation signal can be defined as the transition at precisely 50 percent of the window time. This type of electrical signal can be referred to a class A signal, wherein the zero (or quiescent) level is represented by a voltage level 50 percent of the maximum voltage.

The digital signal can take zero voltage level as the quiescent state and make excursions away from zero in the positive and negative directions as the input analog signal makes similar excursions. This type of signal can be referred to as class B signal. In an electronic device having limited power and supply voltage, a class B signal can be presented to an output transducer through the technique of differential drive. In the technique of differential drive, two outputs having an inverse relationship with one another are connected to one of the terminals of the output transducer. Connection in this manner effectively doubles the signal voltage supplied to the output transducer.

Driving the output transducer with a simple inverse of one terminal's signal at the opposite terminal will result in a drive signal that integrates to zero during the quiescent point. The drive signal will also contain significant energy at the switching frequency. Although analog filter circuitry may be provided to block the energy at the switching frequency, such circuitry may use components that increase the size of the device.

Instead of filters, the inverted output signal 602 can be shifted by 50 percent of the switching window as indicated by diagonal arrows 610. In the quiescent case, the transition points 603, 605 of signal A will align with transition points 604, 606 of signal B and the levels of the signals will be identical, resulting in zero voltage (A minus B) applied to the terminals of the output transducer.

Alternatively to applying the resulting voltage to the output transducer, the signals can be applied to at least two electrodes configured for placement at least partially within the cochlea of the user, such that the user perceives sound in response to electrical stimulation of the cochlea in response to the light output, as described above.

FIG. 7 shows a pair of complementary class B signals. When the analog output voltage moves above zero, the transition 705 of output signal A 701 moves earlier and occurs before fixed transition 604 of the inverted output signal B 702. The high to low transition 706 of the inverted signal B will occur before the fixed transition 603 of the signal A 701.

The differential output A minus B 713 therefore comprises a positive pulse 707 of width equal to the time difference between times 705 and 604 and a positive pulse 708 of width equal to the time difference between times 706 and 603. When the time differences are equal, the widths of pulses 707 and 708 are equal, and the integrated output voltage Vint 709 is a positive voltage as described above.

When the analog voltage signal is below zero, the transition 703 of output signal A 701 moves later than the fixed transition time 604 of signal B 702, and in a similar fashion transition time 704 of signal B moves later than the fixed transition time 603 of signal A 701. In this case, the differential output A minus B 713 comprises negative pulses 710, 711. The duration of pulse 710 is the time difference between variable time 703 and fixed time 604. The duration of pulse 711 is the time difference between variable time 704 and fixed time 603. The integrated result Vint moves from a positive level 709 defined by the duty cycles of pulses 707 and 708 and a negative level 712 defined by the duty cycle of pulses 710 and 711.

At least some embodiments of the output transducer support electronic circuitry so that the light output signal can be transmitted as pulses defining the transition times of a pulse-width modulated signal, with the transducer signal toggled with each transition event. Depending upon the time response of the transmission and reception path, the duration of the transmitted pulses can be small. Many embodiments include a first high-speed signal transmission path and a second path to transmit power.

Alternatively to coupling the circuitry to an output transducer, the above signals and first high-speed transmission path and second path to transmit power can be coupled to at least two electrodes configured for placement at least partially within the cochlea of the user, such that the user perceives sound in response to electrical stimulation of the cochlea in response to the light output, as described above.

FIG. 8 shows a PWM signal 701 as previously described, which comprises a single pulse-width modulated signal generated by a PWM driver, as described above. High-to-low transitions 812 occur at fixed times and low-to-high transitions 813 occur at times which vary according to the analog output level. Each transition initiates a constant width pulse 815 from the circuitry that produces signal 821. Trailing edges 814 of the pulses may occur a constant time after their initiation, or at a time which is adjusted to provide intended effects. The signal 821 controls the emission of light from an emitter. At the receiver, the leading edge 816 of the light pulses triggers a toggle circuit which regenerates the signal 701 or an inverse 826 of the signal 701.

FIG. 9 shows circuitry configured to implement the logic and process the optically transmitted signal, as described above with reference to FIG. 8. PWM signal 701 triggers a pulse generator 902 which is configured to produce a constant-width pulse on its output 904 for each toggle of its input 701, for example constant width pulse 815. Light emitter 908 is driven by the pulse output 904 and the light pulses generated are conducted over light path 909 to high-speed light detector 910 and power generating photovoltaic detector array 917, which may comprise a series array of photovoltaic cells.

The signal 911 generated by light detector 910 is connected to the clock input of D-type flip-flop 912, for example similar to the known 7474 type logic circuits, in which the output 914 is configured to adopt the level of the input 913 upon the rising edge of the clock input 911. A complementary output 918 is configured to adopt the opposite level to the output 914. Such a circuit comprises a toggle when the input 913 is connected to the complementary output 918. The state of output 914, 918 will exchange each time a rising signal edge is presented at clock input 911.

The rising signal edge is presented at clock input 911 by the operation of photodetector 910, shown in FIG. 9 as a reverse-biased photodiode. Power to enable operation of the flip-flop 912 and to provide reverse bias for the photodiode 910 is collected from the light stream by photovoltaic detector array 917 and presented on signal 916 to the circuitry. A power storage device such as a battery or a capacitor 919 can be connected in parallel with photodetector 917 to provide power to flip-flop 912. The power storage device may comprise a miniature rechargeable battery. The voltage presented by photovoltaic detector array 917 may be varied by adjusting the width of pulses generated by pulse generator 902.

Output transducer 915 is connected between the output 914 of the flip-flop 912 and its complementary output 918. An effect of doubling the signal voltage is seen by transducer 915.

Alternatively to coupling the circuitry to transducer 915, the above circuitry can be coupled to at least two electrodes configured for placement at least partially within the cochlea of the user, such that the user perceives sound in response to electrical stimulation of the cochlea in response to the light output, as described above.

FIG. 10 shows an output transducer assembly configured to operate with two light output channels, for example a first channel 520 and a second channel 521 as described above with reference to FIG. 5. Each light output channel may be exclusive to one of photodetectors 1001 or 1002. Photodetectors 1001 and 1002 are connected in parallel. Due to the integrating characteristics of photodetectors 1001 and 1002, a bipolar analog voltage is produced.

The output light channels can transmit many kinds of light signals, for example signal A 701 and signal B 702 as described above, to generate the bipolar analog voltage. The pulse width modulated signal A and signal B from the PWM driver may comprise many known PWM signals, for example at least one of a delta PWM signal, a differential drive PWM signal, a delta-sigma PWM signal or a differential delta-sigma PWM signal. In some embodiments, light power transmission can be minimized with logic circuitry. For example logic circuitry configured to determine a first condition comprising A and Not B of signal A and signal B and a second condition comprising B and Not A of signal B and signal A. The output from the first condition can drive the first light source and the output from the second condition can drive the second light source, such that energy transmitted with the first and second light source is minimized.

Light from both light channels is made available to power photodetectors 1001 and 1002. Negative terminal 1005 of power photodetector array 1001 is connected as the power return from amplifier 1008. Positive terminal 1003 of the power photodetector array 1001 and 1002 is connected to the positive power supply to amplifier 1008. The center terminal 1004 of the photodetector array is connected as the signal return from the output transducer 1012 and signal photodetectors 1009, 1010 Capacitors 1006 and 1007 are connected in parallel with photodetectors 1001 and 1002, respectively. A power storage device, for example at least one of a miniature rechargeable battery or a capacitor, can be connected across positive terminal 1002 and negative terminal 1005 in parallel with photodetector array 1001 to power amplifier 1008. Capacitors 1006, 1007 may provide the energy storage capability.

Light impinging on the power photodetector array 1001, 1002 generates a positive voltage difference which powers amplifier 1008. Light impinging upon signal photodetector 1009 generates a negative signal at the input 1011 to amplifier 1008, and in a like fashion, light impinging upon photodetector 1010 will generate a positive signal voltage at the input 1011 to amplifier 1008.

Amplifier 1008 produces a signal voltage on output conductor 1013, which is connected to output transducer 1012. Current flows from capacitor 1006 through positive supply conductor 1003, through amplifier 1008 into output transducer 1012 and then flows out on conductor 1004 to the junction of capacitors 1006 and 1007. This current flow charges capacitor 1007 and discharges capacitor 1006.

When the output polarity reverses, current flows from the junction of capacitors 1006 and 1007 through conductor 1004, through output transducer 1012, through amplifier 1008 and return conductor 1005 to capacitor 1007. This current flow charges capacitor 1006 and discharge capacitor 1007. Charge loss can be minimized while driving current though the output transducer 1012.

Power photodetectors 1001 and 1002 act to recharge capacitors 1006 and 1007. Power photodetectors 1001 and 1002 may be series-connected arrays as necessary to provide adequate operating voltage to amplifier 1008, which may incorporate such circuitry as is necessary to accept and amplify bipolar input signals on input 1011. Capacitor 1006 may be replaced and/or combined with a miniature Li-Ion or other rechargeable battery. First power photodetector 1001 and second power photodetector 1002 may each comprise at least one photovoltaic material such as crystalline silicon, amorphous silicon, micromorphous silicon, black silicon, cadmium telluride, copper indium, or gallium selenide. In many embodiments, at least one of first power photodetector 1001 or second power photodetector 1002 comprises black silicon, for example as described in U.S. Pat. Nos. 7,354,792 and 7,390,689 and available under from SiOnyx, Inc. of Beverly, Mass., as described above.

Alternatively coupling the above circuitry to transducer 1012, the above circuitry can be coupled to at least two electrodes configured for placement at least partially within the cochlea of the user, such that the user perceives sound in response to electrical stimulation of the cochlea in response to the light output, as described above.

The above circuits may be configured to bias a photo voltaic such as black silicon so as to optimize the absorption and efficiency of the photovoltaic transducer. For example a biased black silicon photovoltaic can be used for power with a fast photo sensor, such as a reverse biased photodiode, used for signal reception.

FIG. 10A shows PWM pulses biased in response to energy of the audio signal. First pulses 1060 comprise a low frequency bias, for “DC” bias that changes slowly, for example in response to low pass filtering of the audio signal. The pulses can be combined with the bias, for example with addition, such that an amplitude 1062 of the pulses imposed on the bias remains substantially constant. In response to the energy of the first pulses 1060, the circuitry can adjust the bias, for example increase the bias in response to an increase in energy, for example power, of the audio signal. Second pulses 1070 comprise a second amplitude 1072 that is substantially similar to first amplitude 1062 first pulses 1060. Second bias 1074 is adjusted in response to energy of first pulses 1060, such that second bias 1074 differs substantially from first bias 1064 so as to accommodate the power consumption of the active circuitry and transducer components.

FIG. 10B shows PWM pulses with amplitudes adjusted in response to energy of the audio signal. First pulses 1080 comprise a first amplitude 1082 and second pulses 1090 comprise a second amplitude 1092 differs substantially from first amplitude 1082 so as to accommodate the power consumption of the active circuitry and transducer components.

FIG. 10C shows voltage to a second light source configured to transmit power to the active circuitry components and transducer, so as to accommodate the power consumption of the these components. A first amplitude 1097 is configured to provide sufficient power for first energy of the audio signal, for example first power of the audio signal. A second amplitude 1099 is configured to provide sufficient power for second energy of the audio signal, for example second power of the audio signal.

FIG. 11 shows a method 1100 of transmitting sound to a user. A step 1105 inputs an audio signal to an input transducer. A step 1110 measures the audio signal. A step 1115 processes the audio signal. The processing can be analog, or digital, or a combination thereof. A step 1120 determines an amount of power of the audio signal. For example with a digital sound processor or with an analog low pass filter, for example. A step 1125 adjusts output in response to the audio signal. The output can be adjusted in many ways, for example with at least one of a DC bias, a sliding scale or an amount of power of a separate channel. A step 1130 determines PWM pulses in response to the audio signal. A step 1135 drives at least one light source in response to the PWM signal and adjustment. A step 1140 transmits the transmits light from the at least one source. A step 1145 filters the transmitted light with filters. A step 1150 detects light with detectors. A step 1155 stores transmitted energy for the active circuitry with a storage device. A step 1160 drives the transducer in response to the PWM signal and the stored energy. With step 1165 a user hears the transmitted audio sound.

Many of the steps of method 1100 can be implemented with the audio processor, described above. For example, the tangible medium of the audio processor may comprise instructions of a computer program embodied therein to implement many of the steps of method 1100.

It should be appreciated that the specific steps illustrated in FIG. 11 provides a particular method transmitting an audio signal, according to some embodiments of the present invention. Other sequences of steps may also be performed according to alternative embodiments. For example, alternative embodiments of the present invention may perform the steps outlined above in a different order. Moreover, the individual steps illustrated in FIG. 8 may include multiple sub-steps that may be performed in various sequences as appropriate to the individual step. Furthermore, additional steps may be added or removed depending on the particular applications. One of ordinary skill in the art would recognize many variations, modifications, and alternatives.

While the above is a complete description of the preferred embodiments of the invention, various alternatives, modifications, and equivalents may be used. Therefore, the above description should not be taken as limiting in scope of the invention which is defined by the appended claims.

	Number	Date	Country
	61139520	Dec 2008	US
	61073281	Jun 2008	US

	Number	Date	Country
Parent	14988304	Jan 2016	US
Child	15411880		US
Parent	14219076	Mar 2014	US
Child	14988304		US
Parent	12486116	Jun 2009	US
Child	14219076		US

OPTICAL ELECTRO-MECHANICAL HEARING DEVICES WITH SEPARATE POWER AND SIGNAL COMPONENTS

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