Patent ID: 12192706

DETAILED DESCRIPTION OF THE INVENTION

FIG.1is a cutaway view of an ear canal showing a contact hearing system110for use in systems and methods according to the present invention, wherein at least a portion of the contact hearing system110is positioned in the ear canal. In embodiments of the invention, contact hearing system110may be referred to as a smartlens system or smartlens. In embodiments of the invention, contact hearing system110may comprise a contact hearing system using electromagnetic waves to transmit information and/or power from ear tip120to the contact hearing device112. In embodiments of the invention, contact hearing system110may comprise a contact hearing system using inductive coupling to transmit information and/or power from ear tip120to contact hearing device112. InFIG.1, contact hearing system110includes Audio processor132, which audio processor may include at least one external microphone310. Audio processor132may be connected to an ear tip120by cable260, which is adapted to transmit signals from audio processor132to ear tip120. Ear tip120may further include canal microphone312and at least one acoustic vent338. Ear tip120may be an ear tip which radiates electromagnetic waves142in response to signals from audio processor132. Electromagnetic signals radiated by ear tip120may be received by contact hearing device112, which may comprise receive coil130, microactuator140, and umbo platform220. As used herein, receive coil130may comprise receive circuit assembly1084as illustrated inFIGS.44-46.

FIG.2is a block diagram of a contact hearing system110for use in methods and apparatus according to the present invention. In embodiments of the invention, at least a portion of contact hearing system110is positioned in the ear canal of a user. InFIG.2, ambient sound340may be received by external microphone310of audio processor132, which then processes the received sound by passing it through processing circuitry, which may include analog to digital converter320and digital signal processor330. The output of audio processor132may be transmitted to an ear tip120by cable260. Signals transmitted to ear tip120may then be transmitted to contact hearing device112by, for example, causing transmit coil290to radiate electromagnetic waves142. In embodiments of the invention, contact hearing device112may include receive coil130, microactuator140, and umbo lens220. Information contained in electromagnetic waves142received by receive coil130may be transmitted through demodulator116to microactuator140, moving umbo lens220. In embodiments of the invention, the signal transmitted to ear tip120may be a signal representative of the received audio signal which may then be transmitted to contact hearing device112. In embodiments of the invention, transmit coil290may be wound around an acoustic vent338in ear tip120. In embodiments of the invention, acoustic vent338may be formed as a passage through a ferrite material or a ferromagnetic material. As used herein ferrite material may be any ferromagnetic material. In embodiments of the invention, transmit coil290may be wound around ferrite material positioned in ear tip120. In embodiments of the invention, contact hearing system110may include one or more external communication and control devices324, such as, for example, a cell phone. In embodiments of the invention, audio processor132may communicate with external communication and control devices324by, for example, using audio processor antenna134.

FIG.3is a top view of a contact hearing device112according to the present invention.FIG.4is a bottom view of a contact hearing device112according to the present invention. The contact hearing device112illustrated inFIGS.3and4includes a receive coil130, a microactuator140, an umbo lens220, a support structure141, and springs144. In the embodiment illustrated inFIGS.3and4, microactuator140is connected to support structure141by springs144. In embodiments of the invention, contact hearing device112may further include a sulcus platform118, which may also be referred to as a mounting platform, connected to support structure141and adapted to assist in positioning contact hearing device112in the ear canal of a user. In embodiments of the invention, contact hearing device112may further include grasping tab114.

FIG.5is a side view of a portion of a contact hearing device112according to the present invention, including a drive post124and umbo lens220. InFIG.5, contact hearing device112, including a drive post124and umbo lens220. InFIG.5, drive post124may be attached to umbo lens220by adhesive122. Drive post124may be attached to the output of microactuator140, which is supported on contact hearing device112by support structure141.

FIG.6is a cutaway view of an ear canal illustrating the positioning of a contact hearing device112according to the present invention. In the embodiment ofFIG.6, contact hearing device112is positioned at a medial end of the ear canal, proximate the tympanic membrane of the user. Contact hearing device112includes a receive coil130positioned at a medial end thereof. In embodiments of the invention, receive coil130may be positioned to receive signals from an ear tip (not shown) positioned in the ear canal lateral to the position of contact hearing device112. In embodiments of the invention, signals received by receive coil130may be transmitted to microactuator140to move drive post124which is connected to the user's tympanic membrane through umbo lens220. Umbo lens220may be in direct physical contact with the tympanic membrane or a thin layer of oil126may be used between umbo lens220and the user's tympanic membrane. Sulcus platform118may be used to properly position contact hearing device112in the user's ear canal through contact with a skin layer which lines the ear canal. Sulcus platform118may be in direct contact with the skin of the ear canal or a thin layer of oil126may be used between sulcus platform118and the skin of the ear canal. In embodiments of the invention contact hearing device112may further include support structure141, grasping tab114, and springs144.

FIG.7illustrates an audio processor132and ear tip120according to the present invention. Ear tip120may, in some embodiments of the invention, be referred to as a mag tip or magnetic tip. In the embodiment ofFIG.7, audio processor132may include external microphones310and volume/control switch314. In embodiments of the invention, ear tip120may include a transmit coil290which may include ferrite core318. In embodiments of the invention, ear tip120may include an acoustic vent which may pass through transmit coil290and/or through ferrite core318

FIG.8is a side perspective view of a transmit coil290for use in an ear tip120according to the present invention. In the embodiment ofFIG.8, transmit coil290includes coil winding316which is wound around ferrite core318. In embodiments of the invention, transmit coil290may further include acoustic vent338. In embodiments of the invention, transmit coil290may further include transmit electronics342. In embodiments of the invention, transmit coil290may be connected to audio processor132by cable260.

FIG.9is an end view of an ear tip120according to the present invention.FIGS.10and10Aare cut away side views of an ear tip according to the present invention.FIG.11is an end view of an ear tip120according to the present invention.FIGS.12and12Aare cut away side views of an ear tip120according to the present invention. In the embodiments ofFIGS.9,10,10A,11,12, and12A, ear tip120includes mounting recess334, which is adapted to receive transmit coil290(shown inFIGS.10A and12A). In the embodiments ofFIGS.9-12, ear tip120further includes at least one secondary acoustic vent336. In embodiments of the invention, secondary acoustic vents are adapted to work in conjunction with acoustic vent338in transmit coil290to reduce the overall acoustic mass of the ear tip. In embodiments of the invention, secondary acoustic vents336combine at central chamber332which has a larger cross section than the combined cross section of secondary acoustic vents336. In embodiments of the invention, secondary acoustic vents336and acoustic vent338combine at central chamber332which has a larger cross section than the combined cross section of secondary acoustic vents336and acoustic vent338.

In embodiments of the invention, the total combined acoustic mass (including the acoustic mass of acoustic vent338through ferrite core318of transmit coil290, the acoustic mass of any secondary acoustic vents336and the acoustic mass of central chamber332) will not exceed 2000 Kg/m4. In embodiments of the invention, the acoustic mass may be defined as the impeding effect of inertia upon the transmission of sound in a conduit, equal in a tubular conduit (as an organ pipe) to the mass of the vibrating medium divided by the square of the cross section. It may also be the acoustic analogue of alternating-current-circuit inductance (called also inertance). In an ear tip which incorporates one or more acoustic vents, the acoustic mass may be representative of the resistance to the flow of air through the ear tip. The acoustic impedance (Z) is frequency specific and relates to the acoustic mass (or inertance, L) as a function of frequency Z=jwL. Acoustic mass may be a function of the cross section of any acoustic vents in an ear tip. Acoustic mass may be a function of the effective length of the acoustic vents in an ear tip. A higher acoustic mass may be perceived by the hearing aid user in a fashion similar to what would be perceived when talking with one's fingers in the ear canals. Thus, a higher acoustic mass effect may be perceived to result in altering the hearing aid user's voice in ways which the hearing aid user finds to be bothersome or unacceptable.

For an even straight tube, the acoustic mass is given by the simple equation:

ρ⁢lA

Where ρ is the density of air (in kg/m3), l is the length of the tube, and A is the cross sectional area along the open bore.

For complex openings, the acoustic mass can be described as the integral of the density of air (ρ) divided by the open cross sectional area along the length of the light tip:

∫ϰ=0tip⁢⁢length⁢ρA⁢r⁢e⁢aϰ⁢d⁢x

Which can be estimated by dividing the tip along its length into n cross sections and summing each open area as follows:

∑i=0n⁢ρA⁢r⁢e⁢ai⁢x⁢Δ⁢l

Where:

Δ⁢l=tip⁢⁢lengthn

In one embodiment, the present invention is directed to an ear tip having a proximal end and a distal end, the eartip including: a transmit coil, the transmit coil including a core of a ferromagnetic material, the ferromagnetic core having a central channel there through, a distal end of the ferromagnetic core positioned at a first opening in a distal end of the ear tip; a passage extending from an opening at a proximal end of the ear tip to the distal end of the ear tip, the passage ending at a second opening in the distal end of the ear tip, wherein a proximal end of the central channel is connected to the passage. In embodiments of the present invention, the combination of the central channel and the passage act as an acoustic vent, allowing air and sound to pass through the ear tip. In embodiments of the present invention, the acoustic vent has a predetermined acoustic mass. In embodiments of the present invention, the predetermined acoustic mass of the ear tip is less than 2000 kilograms per meter4(meter to the fourth power). In embodiments of the present invention, the transmit coil includes a coil winding wound around the ferromagnetic material.

In one embodiment, the present invention is directed to a method of acoustically connecting a proximal end of an ear tip to a distal end of an ear tip wherein the ear tip includes a transmit coil wrapped around a core, the core having an central channel extending from a proximal end of the core to a distal end of the core, and the ear tip having a passage extending from a proximal end of the ear tip to a distal end of the ear tip, the method including the steps of: passing an electrical current through the transmit coil; passing acoustic signals through the central channel; and passing acoustic signals through the passage. In embodiments of the present invention, the acoustic signals comprise sound. In embodiments of the present invention, sound and air pass through the passage. In embodiments of the present invention, a proximal end of the central channel connects to the passage at a point within the ear tip. In embodiments of the present invention, a distal end of the central channel is connected to a first opening in the distal end of the ear tip and the distal end of the passage is connected to a second opening in the distal end of the ear tip.

FIG.13Ais a top perspective view of a charging station136for use in charging audio processors132.FIG.13Bis a back perspective view of a charging station136, including AC adapter port134for use in charging audio processors132. InFIGS.13A and13B, audio processors132may be positioned in charging slots138. Charging status LEDs128may be used to communicate the charge status of audio processors132positioned in charging slots138.

FIG.14is a block diagram of an inductively coupled contact hearing device112and ear tip120according to the present invention. In embodiments of the invention, contact hearing device112may also be referred to as a medial ear canal assembly. InFIG.14, the output of ear tip120may be inductively coupled through transmit coil290to receive coil130on contact hearing device112. In embodiments of the invention, ear tip120may be referred to as a lateral ear canal assembly. In embodiments of the invention, inductive coupling may induce a current in receive coil130on contact hearing device112. In embodiments of the invention, the inductively induced current may be measured by current sensor852. In embodiments of the invention, inductive coupling may induce an output voltage V1across receive coil130. In embodiments of the invention, the induced output voltage may be measured by a voltage meter863. In embodiments of the invention, the measured current and voltage may be used by MPPT control848and data acquisition circuit846. In embodiments of the invention, the output of receive coil130may be further connected to a rectifier and converter circuit865through capacitor854. In embodiments of the invention, receive coil130may be connected directly to rectifier and converter circuit865(eliminating capacitor854). In embodiments of the invention, receive coil130may be connected to a rectifier circuit. InFIG.14, capacitor854may be positioned between the output of receive coil130, which may include capacitor872, and the input of rectifier and converter circuit865. The output of rectifier and converter circuit865may be connected to load882and to storage device869. In embodiments of the invention, rectifier and converter circuitry865may include circuitry which provides power to storage device869and transmits power from storage device869to load882when required. In embodiments of the invention, storage device869may be connected directly to receive coil130or to other circuitry adapted to harvest energy from receive coil130and deliver energy to load882. Load882may be, for example, a microactuator positioned on the contact hearing device112such that load882vibrates the tympanic membrane of a user when stimulated by signals received by receive coil130. Storage device869may be, for example, a rechargeable battery.

In embodiments of the invention, transmit coil290may comprise a transmit coil, such as, for example, transmit coil290and coil130may comprise a receive coil, such as, for example, receive coil130. In embodiments of the invention, transmit coil290and receive coil130may be elongated coils manufactured from a conductive material. In embodiments of the invention, transmit coil290and receive coil130may be stacked coils. In embodiments of the invention, transmit coil290and receive coil130may be wound inductors. In embodiments of the invention, transmit coil290and receive coil130may be wound around a central core. In embodiments of the invention, transmit coil290and receive coil130may be wound around a core comprising air. In embodiments of the invention, transmit coil290and receive coil130may be wound around a magnetic core. In embodiments of the invention, transmit coil290and receive coil130may have a substantially fixed diameter along the length of the wound coil.

In embodiments of the invention, rectifier and converter circuit865may comprise power control circuitry. In embodiments of the invention, rectifier and converter circuit865may comprise a rectifier. In embodiments of the invention, rectifier and converter865may be a rectifying circuit, including, for example, a diode circuit, a half wave rectifier or a full wave rectifier. In embodiments of the invention, rectifier and converter circuit865may comprise a diode circuit and capacitor. In embodiments of the invention, energy storage device869may be a capacitor, a rechargeable battery or any other electronic element or device which is adapted to store electrical energy.

InFIG.14, the output of MPPT control circuit848may control rectifier and converter circuit865. Rectifier and converter circuit865may supply energy to and receive energy from storage device869, which may be, for example, a rechargeable battery. Data acquisition circuit846and rectifier and converter circuit865may be used to drive load882, with data acquisition circuit846proving load882with control data (e.g. sound wave information) and rectifier and converter circuit865providing load882with power. In embodiments of the invention, rectifier and converter circuit865may be used to drive load882directly, without information from a data circuit such as data acquisition circuit846. In embodiments of the invention, rectifier and converter circuit865may be used to drive load882directly without energy from storage device869. The power provided by rectifier and converter circuit865may be used to drive load882in accordance with the control data from data acquisition circuit846. Load882may, in some embodiments of the invention, be a transducer assembly, such as, for example, a balanced armature transducer.

In embodiments of the invention, information and/or power may be transmitted from ear tip120to contact hearing device112by magnetically coupling transmit coil290to receive coil130. When the coils are inductively coupled, the magnetic flux generated by transmit coil290may be used to generate an electrical current in receive coil130. When the coils are inductively coupled, the magnetic flux generated by transmit coil290may be used to generate an electrical voltage across receive coil130. In embodiments of the invention, the signal used to excite transmit coil290on ear tip120may be a push/pull signal. In embodiments of the invention, the signal used to excite transmit coil290may have a zero crossing. In embodiments of the invention, the magnetic flux generated by transmit coil290travels through a pathway that includes a direct air pathway that is not obstructed by bodily components. In embodiments of the invention, the direct air pathway is through air in the ear canal of a user. In embodiments of the invention, the direct air pathway is line of sight between ear tip120and contact hearing device112such that contact hearing device112is optically visible from ear tip120.

In embodiments of the invention, the output signal generated at receive coil130may be rectified by, for example, rectifier and converter circuit865. In embodiments of the invention, a rectified signal may be used to drive a load, such as load882positioned on contact hearing device112. In embodiments of the invention, the output signal generated at receive coil130may contain an information/data portion which includes information transmitted to contact hearing device112by transmit coil290. In embodiments of the invention, at least a portion of the output signal generated at receive coil130may contain energy or power which may be scavenged by circuits on contact hearing device112to charge, for example, storage device869.

FIG.14Ais a block diagram of an inductively coupled contact hearing system according to the present invention. InFIG.14A, contact hearing system110includes Ear Tip120(which may also be referred to as a Mag Tip) and contact hearing device112. Ear Tip120may include a transmit coil290. Contact hearing device112may include receive coil130, parasitic capacitance872, capacitor854, rectifier and converter circuit865and load882.

FIG.15is a block diagram of a contact hearing system110, including a ear tip120(which may also be referred to as a processor) and contact hearing device112according to the present invention. InFIG.15, ear tip120may include an external antenna802adapted to send and receive signals from an external source such as a cell phone (seeFIG.2). External antenna802may be connected to a circuit for processing signals received from external antenna802, such as blue tooth circuit804, which, in some embodiments, may be a blue tooth low energy circuit. The output of Bluetooth circuit804may be connected to digital signal processor840, which may also include inputs from microphones810. Ear canal assembly12may further include battery806and power conversion circuit808along with charging antenna812(which may be a coil) and wireless charging circuit814. Digital signal processor840may be connected to interface circuit816, which may be used to transmit data and power from ear tip120to contact hearing device112. In embodiments of the invention, power and data may be transmitted between ear tip120and contact hearing device112over power/data link818by inductive coupling to provide transmission of the data and power. Alternatively, separate modes of transmission may be used for the power and data signals, such as, for example, transmitting the power using radio frequency or light and the data using inductive coupling.

InFIG.15, power and data transmitted to contact hearing device112may be received by interface circuit822. Interface circuit822may be connected to energy harvesting and data recovery circuit824and to electrical and biological sensors823. InFIG.2, contact hearing device112may further include energy storage circuitry826, power management circuitry828, data and signal processing circuitry832, and microcontroller834. Contact hearing device112may further include a driver circuit836and a microactuator838. In the illustrated embodiment, data transmitted from contact hearing device112may be received by interface circuit816on ear tip120.

FIG.16is a block diagram of a contact hearing system110, adapted for communication with external devices according to the present invention. InFIG.3, contact hearing system110is adapted to communicate with external devices such as cell phone844or cloud computing services842. Such communication may occur through, for example, external antenna802on ear tip120or, in some embodiments directly from contact hearing device112.

FIG.17is a block diagram of a contact hearing device112according to an embodiment of the present invention. InFIG.17, contact hearing device112includes interface720, clock recovery circuit730, data recovery circuit740and energy harvesting circuit750. In embodiments of the invention, interface720is adapted to transmit data from contact hearing device112and to receive data transmitted to contact hearing device112. Interface720may be an inductive interface. Contact hearing device112may further include power management circuit760, voltage regulator770, driver780, data processor encoder790and data/sensor interface800.

InFIG.17, upstream data702collected from data processor/encoder790may be transmitted via interface720as a part of upstream signal700. Downstream signal710may be transmitted to interface720, which may extract the data portion and may distribute downstream data712to data recovery circuit740and clock recovery circuit730. Interface720may further transmit at least a portion of downstream signal710to energy harvesting circuit750. The output of energy harvesting circuit750may be transmitted to power management circuit760, which may then distribute energy to voltage regulator770. Voltage regulator770may distribute its output to driver780, which may also receive input from data recovery circuit740. The output of driver780may be sent through matching network831to drive, for example, microactuator840.

Microactuator840may include sensors (not shown) which generate data about the function of microactuator840. This data may be transmitted back to contact hearing device112through matching network831and to data/sensor interface800, which, in turn may transmit the sensor information to data processor/encoder790, which generates upstream data702. Data/sensor interface800may also receive information from other sensors (e.g. Sensor1to Sensor n inFIG.4), which data is, in turn, transmitted to data processor/encoder790and becomes part of upstream data702.

FIG.18is a diagram of a rectifier and converter circuit865according to the present invention. InFIG.18, rectifier and converter circuit865may include diode974and capacitor972. In embodiments of the invention, the input to rectifier and converter circuit865may be connected directly to receive coil130. In embodiments of the invention, the output of rectifier and converter circuit865may be coupled directly to a load, such as, for example, a transducer or a balanced armature transducer. In embodiments of the invention, the output of rectifier and converter circuit865may be coupled to the windings in a load, such as, for example, a transducer or a balanced armature transducer.

FIG.18Ais a diagram of a rectifier and converter circuit865according to the present invention. In embodiments of the invention, rectifier and converter circuit865may comprise a Villard Circuit. In embodiments of the invention, rectifier and converter circuit865may be a voltage multiplier circuit. InFIG.18, rectifier and converter circuit865may include diode974, AC filter capacitor975(which may be a series capacitor) and resonant capacitor977. In embodiments of the invention, the input to rectifier and converter circuit865may be connected directly to receive coil130. In embodiments of the invention, the output of rectifier and converter circuit865may be coupled directly to a load, such as, for example, a transducer or a balanced armature transducer. In embodiments of the invention, the output of rectifier and converter circuit865may be coupled to the windings in a load, such as, for example, a transducer or a balanced armature transducer.

FIG.19is a diagram of an alternative rectifier and converter circuit865according to the present invention. In embodiments of the invention, rectifier and converter circuit865may include diodes974and capacitors972which may form, for example bridge circuits such as, for example a half wave bridge.

FIG.20is a diagram of an alternative rectifier and converter circuit according to the present invention. In embodiments of the invention, rectifier and converter circuit865may include diodes974and capacitors972which may form, for example bridge circuits such as, for example, a full wave bridges. In embodiments of the invention, rectifier and converter circuit865may be connected to receive coil130.

FIG.21is a diagram of a portion of a contact hearing device112according to the present invention. In embodiments of the invention, the input to rectifier and converter circuit865may be connected to receive coil130through additional circuitry, such as, for example, capacitor854or input circuitry976. In embodiments of the invention, the output of rectifier and converter circuit865may be coupled to a load, such as, for example, a transducer or a balanced armature transducer through an output circuit978. In embodiments of the invention, output circuit978may be, for example, a capacitor, an inductor, a combination of electrical or electronic components and/or a matching circuit.

FIG.21Ais a diagram of a portion of a contact hearing device according to the present invention. InFIG.21A, contact hearing device112may include receive coil130, connected to rectifier and converter circuit865, which, in turn, may be connected to load882, which may be, for example, a microactuator, for example a balanced armature microactuator.

FIG.22is a circuit diagram of transmitter and receiver components of a contact hearing system110according to embodiments of the present invention. In embodiments of the invention, ear tip120may include a drive circuit988, which may also be referred to as a transmit circuit. Drive circuit988may include coil L1980and signal source996. In embodiments of the invention, ear tip120may further include transmit resonant circuit992. In embodiments of the invention, transmit resonant circuit992may include resonant transmit coil L2994and resonant transmit capacitor C1998. In embodiments of the invention, contact hearing device112may include load circuit990. In embodiments of the invention, load circuit990may include load coil982, voltage detector1002, rectifier1004and load1006. In embodiments of the invention, contact hearing device112may include receive resonant circuit994. In embodiments of the invention, receive resonant circuit994may include resonant receive coil986and resonant receive capacitor C21000.

FIG.22Ais a circuit diagram of transmitter and receiver components of a contact hearing system according to embodiments of the present invention. In the contact hearing system110ofFIG.22A, ear tip120includes drive coil L1980. In the contact hearing system110ofFIG.22A, contact hearing device112includes load coil L4982, resonance capacitor977(which may also be referred to as a tuning capacitor), AC filter capacitor975, rectifier circuit1004and load1006.

In embodiments of the invention, drive coil980may be a transmit coil such as, for example, transmit coil290. In embodiments of the invention, load coil982may be a receive coil such as, for example, receive coil130. In embodiments of the invention, rectifier1004may be a rectifier and converter circuit such as, for example, rectifier and converter circuit865. In embodiments of the invention, load1006may be an actuator, such as, for example microactuator140. In embodiments of the invention, microactuator140may be, for example, a balanced armature microactuator.

FIGS.23and24are circuit diagrams of components of a receiver1016for use in a contact hearing system110according to the present invention. In embodiments of the invention, receiver1016may be constructed in a full-wave rectifier receiver configuration, including a smoothing capacitor. In embodiments of the invention, receiver102includes receive inductor Lrx1008, receive capacitor array1030, diode bridge1032, motor1028, and smoothing capacitor1026. In embodiments of the invention, receive capacitor array1030may include one or more receive capacitors, such as, receive capacitor Cr11010, receive capacitor Cr21012and receive capacitor Cr31014. In embodiments of the invention, diode bridge1034may include one or more diodes, such as, diode D11018, diode D21020, diode D31022, and diode D41024. In embodiments of the invention, diode bridge1034may be arranged as a full wave rectifier bridge with a load, such as, for example, motor1028connected across the output of the full wave rectifier. In embodiments of the invention (such as the one illustrated inFIG.23), a smoothing capacitor Cs1026may be connected across the output of the full wave rectifier in parallel with the motor1028. In embodiments of the invention (such as the one illustrated inFIG.24), the smoothing capacitor may be omitted. In embodiments of the invention, the diodes used in diode bridge1034may be Schottky diodes. In embodiments of the invention, the electrical characteristics of motor1028may be represented by the series circuit which includes motor resistor1030, representing the resistance of the circuitry in motor1028and motor inductor1032, representing the inductance of motor1028at the frequency of operation.

FIG.25is a circuit diagram of components of a transmitter1036for use in a contact hearing system110according to the present invention. In embodiments of the invention, transmitter1036may be a current source1038connected in parallel with one or more output capacitors, such as C01040and output coil L11042. In the embodiment of the invention, illustrated inFIG.25, the transmitter may be a parallel drive with the signal input modeled as current source1038. The configuration illustrated inFIG.25is advantageous because it requires a low input current.

FIG.26is a circuit diagram of components of a transmitter1036for use in a contact hearing system110according to the present invention. In embodiments of the invention, transmitter1036may be modeled as a voltage source1044feeding a capacitive transformer/divider1046through a resistor R11048. In this embodiment, capacitive transformer/divider1046may be modeled as Capacitor C011050in series with capacitor C021052, which are in parallel with inductor L11054. The embodiment of the transmitter, illustrated inFIG.26is advantageous because it may be used to generate a large VL1when V1is small, thus allowing the circuit to be driven by, for example, a battery having a limited output voltage, for example, an output voltage in the range of 3 Volts. In this embodiment, voltage source V11044, in parallel with resistor R11048, combine to form a quasi-current source. In the embodiment illustrated, the resonant frequency will be a function of the series combination of capacitor C011050, capacitor C021052and Inductor L11054.

FIG.27is a circuit diagram of components of a transmitter1036for use in a contact hearing system110according to the present invention. In embodiments of the invention, the circuit illustrated may represent a parallel drive arrangement for transmitter1036. In embodiments of the invention, transmitter1036may be modeled as a voltage source V11044feeding a parallel drive circuit1056. In embodiments of the invention, parallel drive circuit1056may include capacitor C71058, capacitor C11060and inductor L11054. In embodiments of the invention, capacitor C71058adds impedance to voltage source V11044to create a quasi-current source. In embodiments of the invention, C7may be small compared to C11060in order to ensure that most of the tank current flows in the L1-C1loop, rather than in the L1-C7loop. In embodiments of the invention, the resonant frequency will depend on the series combination of inductor L11054with the parallel combination of capacitor C11060and capacitor C71058.

In embodiments of the invention, using inductive coupling for power and/or data transfer in a contact hearing system may result in benefits over other methods of power and/or data transfer, including: reduced sensitivity to directionality; reduced sensitivity to motion in components of the contact hearing system; improved patient comfort; reduced sensitivity to the presence of bodily fluids, including cerumen; reduced sensitivity to the presence of tissue between the ear tip and the contact hearing device; reduced sensitivity to tissue loading; reduced sensitivity to the distance between the ear tip and the contact hearing device. In embodiments of the invention, power and data transfer may be separated (e.g. different frequencies) or combined.

In embodiments of the invention, data and power may be transferred from an ear tip to a contact hearing device using near field magnetic coupling. In embodiments of the invention, data may be transferred from an ear tip to a contact hearing device using near field magnetic coupling. In embodiments of the invention, power may be transferred from an ear tip to a contact hearing device using near field magnetic coupling. In embodiments of the invention, the use of near field magnetic coupling results in a power transfer wherein the power output from the contact hearing device remains relatively constant even when the distance between the ear tip and the contact hearing device varies. In embodiments of the invention, as illustrated inFIG.32, the use of near field magnetic coupling results in a power output wherein the output of the contact hearing device varies by less than 2 dB SPL when the distance between the ear tip and the contact hearing device varies between 3 and 7 millimeters. In embodiments of the invention, as illustrated inFIG.32, the use of near field magnetic coupling results in a power output wherein the output of the contact hearing device varies by less than 2 dB SPL when the distance between the ear tip and the contact hearing device is approximately 3 millimeters. In embodiments of the invention, data and power may be transmitted from an ear tip to a contact hearing device using resonant inductive coupling. In embodiments of the invention, the receive coil and the transmit coil may be connected through resonant inductive coupling. In embodiments of the invention, data and power may be transmitted from an ear tip to a contact hearing device using near field magnetic induction. In embodiments of the invention, data and power may be transmitted from an ear tip to a contact hearing device using a near field magnetic induction link.

In embodiments of the invention, such near field magnetic coupling could also be used to remotely power and/or deliver signal to neuro-stim implants. In embodiments of the invention, the actuator may be replaced by electrodes. In embodiments of the invention, such near field magnetic coupling could also be used to remotely power in-body valves for, for example, bladder control.

In embodiments of the invention, the separation between the transmit coil and the receive coil may be between approximately five and nine millimeters when the system is placed in a user's ear.

In one embodiment, the present invention is directed to a method of transmitting information from an ear tip to a contact hearing device, the method including the steps of: exciting a transmit coil, the transmit coil being positioned in the ear tip, wherein the transmit coil is wound on a core, the core including a ferromagnetic material; radiating an electromagnetic field from the first coil through the ear canal of a user; receiving the radiated electromagnetic field at a receive coil, the receive coil being positioned on a contact hearing device, the contact hearing device including a receive coil without a ferrite core; and transmitting the information from the transmit coil to the receive coil using near-field radiation. In embodiments of the invention, the ear tip includes the transmit coil and the contact hearing device includes the receive coil. In embodiments of the invention, the method includes the step of adapting the ear tip such that it positions the medial end of the transmit coil to be within between 3 and 7 millimeters of the lateral end of the receive coil when the ear tip and contact hearing device are positioned in the ear canal of a user. In embodiments of the invention, the method includes the step of adapting the ear tip such that when it is positioned in the ear canal of a user more than fifty percent of magnetic flux lines emanating from the transmit coil couple through the receive coil. In embodiments of the invention, the method includes the step of adapting the ear tip such that when it is positioned in the ear canal of a user more than seventy five percent of a magnetic field generated by the transmit coil is coupled to the receive coil. In embodiments of the invention, the method includes the step of generating a signal in the transmit coil induces current in the receive coil, wherein the induce current is induced by the presence of a magnetic field generated at the transmit coil. In embodiments of the invention, the current induced is proportional to the magnetic field at the transmit coil. In embodiments of the invention, the step of generating a signal in the transmit coil results in a voltage generated across the receive coil wherein the generated voltage is a product of the magnetic field generated at the transmit coil. In embodiments of the invention, the voltage generated is proportional to the magnetic field at the transmit coil. In embodiments of the invention, the transmitted information is transmitted in an amplitude modulated (AM) signal. In embodiments of the invention, the transmitted information is demodulated by a demodulator attached to a receive coil. In embodiments of the invention, the transmit coil is magnetically coupled to the receive coil. In embodiments of the invention, the coupling between the transmit and receive coils is between approximately 0.1 percent and approximately 3.0 percent. In embodiments of the invention, information and power are transmitted from the transmit coil to the receive coil through the interaction of magnetic fields generated in the transmit coil with the receive coil. In embodiments of the invention, the core includes a ferrite material.

In one embodiment, the present invention is directed to a method of transmitting information from an ear tip to a contact hearing device, the method including the steps of: exciting a transmit coil, the transmit coil being positioned in an ear tip, wherein the transmit coil is wound on a ferrite core; radiating an electromagnetic field from the first coil through the ear canal of a user; receiving the radiated electromagnetic field at a receive coil, the receive coil being positioned on a contact hearing device without a ferrite core; and transmitting the information from the transmit coil to the receive coil using a near-field radiation. In embodiments of the invention, the first and second coils are inductively coupled. In embodiments of the invention, inductive coupling is used to link the first coil to the second coil. In embodiments of the invention, the information is transmitted from the first coil to the second coil using near-field magnetic coupling. In embodiments of the invention, the information is transmitted from the first coil to the second coil using resonant inductive coupling. In embodiments of the invention, the information is transmitted from the first coil to the second coil using near-field magnetic induction. In embodiments of the invention, the information is transmitted from the first coil to the second coil using a near-field magnetic induction link. In embodiments of the invention, the output of the contact hearing device varies by less than two decibels sound pressure level (dB SPL) when the distance between the transmit and receive coils varies by between three and seven millimeters. In embodiments of the invention, the receive coil is a part of a receive coil assembly, the receive coil assembly including: the receive coil; at least one disk positioned at a distal end of the receive coil, the at least one disk including a ferromagnetic material. In embodiments of the invention, the receive coil is wound with a central core of a non-ferromagnetic material. In embodiments of the invention, the non-ferromagnetic material is, at least in part, air. In embodiments of the invention, the outer diameter of the at least one disk is substantially the same as the outer diameter of the receive coil. In embodiments of the invention, the at least one disk includes a hole therethrough. In embodiments of the invention, the at least one disk is two disks. In embodiments of the invention, a printed circuit board including electronic components is affixed to a side of the at least one disk opposite the side to which the receive coil is affixed. In embodiments of the invention, the at least one disk includes a ferrite material.

In one embodiment, the present invention is directed to a method of transmitting information from an ear tip to a contact hearing device, the method including the steps of: exciting a transmit coil, the transmit coil being positioned in an ear tip, wherein the transmit coil is wound on a ferromagnetic core; radiating an electromagnetic field from the transmit coil through an ear canal of a user; receiving the radiated electromagnetic field at a receive coil, the receive coil being positioned on a contact hearing device, the receive coil having a core of a non-ferromagnetic material; and transmitting the information from the transmit coil to the receive coil using the electromagnetic field. In embodiments of the invention, the transmit and receive coils are inductively coupled. In embodiments of the invention, inductive coupling is used to link the transmit coil to the receive coil. In embodiments of the invention, the information is transmitted from the transmit coil to the receive coil using near-field magnetic coupling. In embodiments of the invention, the information is transmitted from the transmit coil to the receive coil using resonant inductive coupling. In embodiments of the invention, information is transmitted from the transmit coil to the receive coil using near-field magnetic induction. In embodiments of the invention, information is transmitted from the transmit coil to the receive coil using a near-field magnetic induction link. In embodiments of the invention, the output of the contact hearing device varies by less than two decibels sound pressure level (dB SPL) when the distance between the transmit and receive coils varies by between three and seven millimeters. In embodiments of the invention, the receive coil is a part of a receive coil assembly, the receive coil assembly including: the receive coil; at least one disk positioned at a distal end of the receive coil, the at least one disk including a ferromagnetic material. In embodiments of the invention, the receive coil is wound with a central core of a non-ferromagnetic material. In embodiments of the invention, the non-ferromagnetic material is, at least in part, air. In embodiments of the invention, an outer diameter of the at least one disk is substantially the same as an outer diameter of the receive coil. In embodiments of the invention, the at least one disk includes a hole therethrough. In embodiments of the invention, the at least one disk is two disks. In embodiments of the invention, a printed circuit board including electronic components is affixed to a side of the at least one disk opposite a side to which the receive coil is affixed. In embodiments of the invention, the electronic components on the printed circuit board include a demodulation circuit. In embodiments of the invention, the demodulation circuit is a diode demodulator. In embodiments of the invention, the at least one disk includes a ferrite material.

In embodiments of the invention, the transmit coil may include a coil with an air core. In embodiments of the invention, the transmit coil may include a coil wound around a ferrite core. In embodiments of the invention, the transmit coil may include a coil wound around a ferrite core with a channel through the center of the ferrite core, the channel forming an opening from the proximal end to the distal end of the ferrite core. The channel may further be positioned and sized to form an acoustic vent, allowing sound to pass through the ferrite core. In embodiments of the invention, the receive coil may include a coil wound around an air core. In embodiments of the invention, the receive coil may include a coil wound around ferrite core.

As illustrated inFIGS.33-35, in embodiments of the invention, the central axis of the receive core and the central axis of the transmit core may be substantially parallel when the ear tip and the contact hearing device are positioned in the ear canal of a user. In embodiments of the invention, the central axis of the receive core and the central axis of the transmit core form an angle of not greater than 15 degrees. In embodiments of the invention, the central axis of the receive core and the central axis of the transmit core form an angle of not more than approximately 25 degrees. In embodiments of the invention, the system has a signal reduction of less than 0.5 dB over an angle of between plus and minus 20 degrees from full alignment.

In embodiments of the invention, a reduction in output (in dB) for a receive coil assembly as a function of the transmit to receive coil angle as a function of the distance L, and the angles θ1, θ2and θ3over a range of ±45°. In embodiments of the invention, the angle θ may be greater than ±45° and distance between the transmit coil and the receive coil may be between 2 and 12 mm.

As illustrated inFIGS.44,45,46A and46B, a receive circuit assembly1084may include receive circuit board1074, which may have mounted thereon receive circuit components1072. Receive circuit assembly may further include receive coil winding (Rx Coil)1080and ferrite disk(s)1078. Ferrite disc(s)1078may be attached to receive circuit board1074by adhesive1076. Receive coil winding1080may include a plug1082at a proximal end thereof. In embodiments of the invention, receive coil winding1080may be wound around a core of a non-ferromagnetic material, such as, for example air. In embodiments of the invention, ferrite disk(s)1078may include a hole in the center of the disks. In embodiments of the invention, the hole in the center of ferrite disk(s)1078may be substantially the same diameter as the core of receive coil winding1080.FIG.46Aillustrates the flux path through receive circuit assembly1084wherein the flux may be generated by an ear tip which is located a distance away from receive circuit assembly1084in the ear canal of a user. In embodiments of the invention, the magnetic flux may be generated in a coil positioned in the ear tip and may be a signal representative of information (e.g. audio information) to be transmitted to a contact hearing device which includes receive circuit assembly1084. InFIG.46Aflux enters receive circuit assembly1084at a proximal end thereof and passes through receive coil winding1080and then through ferrite disk(s)1078. InFIG.46Athe flux passing through receive circuit assembly1084induces a current in receive coil winding1080. In embodiments of the invention, the current induced in receive coil winding1080will be conducted electrical components on contact hearing device112, which will demodulate the received signal and transmit that signal to a microactuator140which may be in contact with the tympanic membrane of a user.

In embodiments of the invention, receive circuit assembly1084includes receive coil windings1080which may be backed by one or more (e.g. two) two ring-shaped ferrite layers (which may also comprise or be referred to as ferrite disk(s))1078to which receive circuit components (e.g. one of the demodulator circuit described herein) are attached. In embodiments of the invention, the ferrite layers may increase the strength of the received signals in multiple ways.

In embodiments of the invention, the ferrite layers may increasing the inductance and Q of receive circuit assembly1084. In embodiments of the invention, the ferrite layers may shunt magnetic flux entering receive coil windings1080to the outside of receive coil windings1080on the distal (PCB) end of receive coil windings1080. In embodiments of the invention, magnetic flux may be shunted because the ferrite layers have high permeability and low reluctance compared to air and PCB material. In embodiments of the invention, this shunting of the magnetic flux results in the magnetic field being coupled more tightly around the receive coil windings1080, which increases inductance without significant effect on the AC resistance. The Q increases directly from its defining equation Q=2πfL/RAC, where f is the carrier frequency and L and RACare the inductance and resistance at the carrier frequency, respectively.

In embodiments of the invention, shunting the field, the ferrite layers also shield receive circuit board1074and receive circuit components1072from the magnetic field and reduce loading of the magnetic field by eddy currents in the metal traces of receive circuit board1075. As a result, the field inside receive coil windings1080is stronger, compared to a receive circuit assembly1084which did not include any ferrite layers (e.g. ferrite disk(s)1078and, therefore, may produce a higher signal strength at the output of receive circuit assembly1084.

In embodiments of the invention, by acting as spacers to separate receive circuit board1074from a distal end of receive coil windings1080decreases magnetic-field loading caused by the presence of receive circuit board1074and receive circuit components1072at the distal end of receive coil windings1080.

In embodiments of the invention, ferrite disk(s)1078may comprise a single layer of ferrite material. In embodiments of the invention, ferrite disk(s)1078may be a ferrite powder embedded in a rubbery matrix. In embodiments of the invention, the ferrite layers, ferrite disks or ferrite rings described herein may be made of any suitable ferromagnetic material.

In embodiments of the invention, the present invention is directed to a contact hearing system including: a transmit coil positioned in an ear tip wherein the transmit coil includes an electrical coil wound on a ferrite core; a receive coil positioned on a contact hearing device wherein the receive coil includes an electrical coil wound on a non-ferrite core. In embodiments of the invention, the non-ferrite core includes air. In embodiments of the invention, the receive coil is a component of a receive coil assembly, the receive coil assembly including at least one ferrite disk positioned at a distal end of the receive coil. In embodiments of the invention, the at least one ferrite disk includes a hole in a center of the at least one ferrite spacer. In embodiments of the invention, the at least one ferrite disk includes a plurality of ferrite disks laminated together. In embodiments of the invention, the at least one ferrite disk includes two or more ferrite disks. In embodiments of the invention, the receive coil includes a first central axis and the at least one ferrite disk includes a second central axis, the first central axis and the second central axis being aligned. In embodiments of the invention, the ferrite core includes a channel extending from a proximal to a distal end thereof. In embodiments of the invention, a central axis of the transmit coil and a central axis of the receive coil are substantially parallel when the ear tip and the contact hearing device are positioned in an ear canal of a user. In embodiments of the invention, a central axis of the transmit coil and a central axis of the receive coil form an angle of approximately 15 degrees or less when the ear tip and the contact hearing device are positioned in an ear canal of a user. In embodiments of the invention, a central axis of the transmit coil and a central axis of the receive coil form an angle of approximately 25 degrees or less when the ear tip and the contact hearing device are positioned in an ear canal of a user. In embodiments of the invention, a distal end of the transmit coil is positioned within between three and seven millimeters of the proximal end of the receive coil.

In embodiments of the invention, the present invention is directed to a contact hearing system, the contact hearing system including: an ear tip, the ear tip including a transmit coil wherein the transmit coil is wound around a core including, at least in part, a ferromagnetic material; and a contact hearing device including a receive coil wherein the receive coil is wound around a core including, at least in part, a non-ferromagnetic material. In embodiments of the invention, the ferromagnetic material includes a ferrite material. In embodiments of the invention, the non-ferromagnetic material includes air. In embodiments of the invention, the contact hearing device includes a receive circuit assembly, the receive circuit assembly including: the receive coil; a disk attached to a distal end of the receive coil wherein the disk includes a ferromagnetic material. In embodiments of the invention, the disk has a diameter which is substantially the same as a diameter of the receive coil. In embodiments of the invention, the disk has a hole in its center. In embodiments of the invention, the receive circuit assembly further includes a printed circuit board including electronic components. In embodiments of the invention, the disk acts as a spacer to separate the printed circuit board from a distal end of the receive coil. In embodiments of the invention, magnetic flux lines entering a proximal end of the receive coil are bent away from the printed circuit board by the disk as they exit a distal end of the receive coil. In embodiments of the invention, at least a portion of magnetic flux lines entering a proximal end of the receive coil are prevented from reaching the printed circuit board as they exit a distal end of the receive coil. In embodiments of the invention, the presence of the disk increases a quality factor (Q) of the receive circuit assembly. In embodiments of the invention, the disk reduces eddy currents in conductive traces on the printed circuit board when magnetic flux is passed through the receive coil. In embodiments of the invention, the printed circuit board includes components of a demodulation circuit.

In embodiments of the invention, the transmit and/or receive coils may be encapsulated using a parylene coating.

In embodiments of the invention, the Q (where Q is defined as the ratio of the energy stored in the resonator to the energy supplied by a to it, per cycle, to keep signal amplitude constant, at a frequency where the stored energy is constant with time) of the transmit circuit (“Tx Q”) is higher than the Q of the contact hearing device (“Rx Q”). In embodiments of the invention, the Tx Q may be greater than or equal to 70 and the Rx Q may be less than or equal to 20. In embodiments of the invention, the Rx Q is maximized by moving all circuitry to a board outside of the Rx coil. In embodiments of the invention, a ferrite core is used to increase the Q of the transmit coil. In embodiments of the invention, the transmit signal is amplified by exciting the transmit coil to a high state of resonance.FIG.52is an illustration of a system according to the present invention wherein a transmit circuit according to the present invention is tuned to have a higher Q than a receive circuit according to present invention. In embodiments of the invention, the transmit circuit may have a Q of between approximately 50 and 75. In embodiments of the invention, the transmit circuit may have a Q of approximately 60. In embodiments of the invention, the receive circuit may have a Q of between approximately 15 and 25.

In one embodiment, the present invention is directed to a contact hearing system including: an ear tip including a transmit circuit having a first Q value, wherein the ear tip includes a transmit coil wound on a ferrite core; a contact hearing device including a receive circuit having a second Q value, wherein the first Q value is greater than the second Q value; a receive coil positioned on the contact hearing device, wherein the receive coil includes a core of a non-ferromagnetic material. In embodiments of the present invention, the first Q value is greater than the second Q value by a factor of at least two. In embodiments of the present invention, the receive coil includes a disk including a ferromagnetic material at a distal end thereof. In embodiments of the present invention, the disk includes a ferrite material. In embodiments of the present invention, the disk includes a hole in its central portion. In embodiments of the present invention, the transmit coil is inductively coupled to the receive coil. In embodiments of the present invention, the contact hearing device includes a diode detector connected to the receive coil. In embodiments of the present invention, the contact hearing device includes a balanced armature microactuator connected to the receive coil. In embodiments of the present invention, the contact hearing device includes a platform which supports the receive coil, wherein the platform conforms to the anatomy of the wearers ear canal. In embodiments of the present invention, the contact hearing device includes a platform which supports the receive coil, wherein the platform is adapted to position the contact hearing device on a wearer's tympanic membrane.

In one embodiment, the present invention is directed to a method of inductively coupling an ear tip having a transmit circuit to a contact hearing device having a receive circuit, wherein the transmit circuit has a first Q value and the receive circuit has a second Q value, the first Q value being greater than the second Q value, the method including the steps of: exciting a transmit coil in the transmit circuit, the transmit coil being positioned in an ear tip; radiating an electromagnetic field from the transmit coil to a receive coil; receiving the radiated electromagnetic field at the receive coil, the receive coil being positioned on a contact hearing device; and transmitting information from the transmit coil to the receive coil using the electromagnetic field. In embodiments of the present invention, the first Q value is at least twice as large as the second Q value. In embodiments of the present invention, the transmit coil includes a ferrite core. In embodiments of the present invention, the receive coil includes a ferrite disk at a distal end thereof. In embodiments of the present invention, ferrite disk includes a hole in its central portion. In embodiments of the present invention, the information is transmitted from the transmit coil to the receive coil using near field radiation. In embodiments of the present invention, the transmit coil is inductively coupled to the receive coil. In embodiments of the present invention, the electromagnetic radiation induces a current in the receive coil. In embodiments of the present invention, the current induced in the receive coil is proportional to a level of magnetic flux passing through the receive coil. In embodiments of the present invention, a current induced in the receive coil drives a balanced armature microactuator positioned on the contact hearing device.

In one embodiment, the present invention is directed to a contact hearing system including: an ear tip including a transmit circuit having a first Q value, wherein the ear tip includes a transmit coil wound on a ferrite core, the first Q being in a range of between fifty and seventy-five; a contact hearing device including a receive circuit having a second Q value, wherein the second Q value is in the range of between fifteen and twenty-five; a receive coil positioned on the contact hearing device, wherein the receive coil has a core of non-ferromagnetic material. In embodiments of the present invention, the receive coil is a component of a receive circuit assembly, the receive circuit assembly including a disk at a distal end of the receive coil, wherein the disk includes a ferromagnetic material. In embodiments of the present invention, the receive coil assembly further includes a printed circuit board, the printed circuit board being separated from the distal end of the receive coil by the disk.

In a standard systems for transmitting information using electromagnetic waves it would be conventional to design the system such that both the transmit and receive circuits were optimized around the carrier frequency, that is that the transmitter would have its highest output at the carrier frequency and the receive circuit would have its most efficient reception at the carrier frequency (e.g. the receive coil or antenna would be optimized to pass signals at the carrier frequency with the least loss). In such a system it would be conventional to tune the transmitter (Tx) and receiver (Rx) resonance, to maximize power transfer. For example, you would tune both circuits to have a maximum Q with the pass band for both the Tx and Rx centered around the carrier frequency. Resonance generally occurs at (Where L is inductance and C is capacitance):

f0=ω02⁢π=12⁢⁢π⁢LC.

Where AM modulation is used, such as in inductively coupled systems according to the present invention, that standard tuning may result in Intermodulation Distortion and/or harmonic distortion. Intermodulation Distortion (IMD) may be defined as the ratio (in dB) between the power of fundamental tones and third-order distortion products which may, under certain circumstances be audible to a listener, for example, a hearing aid user. In a system such as a contact hearing, system IMD may manifest itself as distortion of words and letters which incorporate higher frequency tones (e.g. “S” and “T” sounds). This is a particular problem in such systems because contact hearing systems transmit and deliver those sounds directly to the tympanic membrane through mechanical manipulation of the tympanic membrane, unlike conventional hearing aids.

In embodiments of the present invention, it may be possible to reduce or eliminate such intermodulation distortion by tuning the receive coil to center the passband at a frequency above the frequency of the carrier. In embodiments of the invention, the center of the receive passband may be tuned to approximately 137 KHz above the carrier frequency. In embodiments of the invention, the center of the bandpass may be tuned to approximately 322 KHz above the carrier frequency. Thus, by tuning the Rx circuit in a manner which would be expected to result in lower efficiency (power transfer), the present invention reduces or eliminates intermodulation distortion. In embodiments of the invention, the Rx circuit is tuned such that the new center of the passband is above the carrier frequency while the transmit (Tx) circuit is tuned such that the center of the passband for the transmit (Tx) circuit is below the transmit frequency.

FIG.52is a graph showing passband tuning according to the present invention for a transmit circuit and a receive circuit according to the present invention. InFIG.52a transmit circuit is tuned such that the center of its passband is at the system carrier frequency (e.g. 2.560 MHz), while the receive passband is tuned such that the center of its passband is at a second, higher, frequency (e.g. 2.852). Further, as illustrated inFIG.52the transmit circuit is tuned to have a higher Q than the receive band. In embodiments of the invention, the transmit and receive circuits are tuned to have an offset between the center of the transmit passband and the center of the receive passband in order to improve intermodulation distortion. In embodiments of the invention, the transmit and receive circuits are tuned to have an offset between the center of the transmit passband and the center of the receive passband in order to improve power transmission from the transmitter to the receiver. In embodiments of the invention, the transmit and receive circuits are tuned to have an offset between the center of the transmit passband and the center of the receive passband in order to increase output power at the contact hearing device. In embodiments of the invention, the center frequencies of the receive passband may be lower than the center frequency of the transmit passband.

In embodiments of the invention, the relationship between the transmit passband and the receive passband may be such that a signal at a frequency which is at the center of the transmit passband (e.g. a carrier signal) would be attenuated by between approximately 10 dB and 15 dB if it were passed through a filter having the characteristics of the receive passband. In embodiments of the invention, the relationship between the transmit passband and the receive passband may be such that a signal at a frequency which is at the center of the receive passband would be attenuated by between approximately 20 dB and 25 dB if it were passed through a filter having the characteristics of the receive passband.

In embodiments of the invention, the present invention is directed to a contact hearing system including: a transmit circuit including a transmit coil positioned in an ear tip, THE transmit circuit having a first bandpass characteristic, wherein the transmit circuit is tuned such that a center of the first bandpass characteristic is set at a first frequency; and a receive circuit including a receive coil positioned on a contact hearing device, the receive circuit having a second bandpass characteristic, wherein the receive circuit is tuned such that a center of the second bandpass characteristic differs from the center of the first bandpass characteristic. In embodiments of the invention, the transmit circuit is tuned such that the center of the first bandpass characteristic is a transmit carrier frequency. In embodiments of the invention, the transmit carrier frequency is approximately 2.56 MHz. In embodiments of the invention, the receive circuit is tuned such that the center of the second bandpass characteristic is tuned to a frequency which is higher than the first frequency. In embodiments of the invention, the receive circuit is tuned such that the center of the second bandpass characteristic is tuned to a frequency above a transmit carrier frequency. In embodiments of the invention, the receive circuit is tuned such that the center of the second bandpass characteristic is tuned to approximately 2.852 MHz. In embodiments of the invention, the receive circuit is tuned such that the center of the second bandpass characteristic is tuned to a frequency within 5 percent of the carrier frequency. In embodiments of the invention, the receive circuit is tuned such that the center of the second bandpass characteristic is tuned to a frequency within 10 percent of the carrier frequency. In embodiments of the invention, the receive circuit is tuned such that the center of the second bandpass characteristic is tuned to a frequency which is within the bandpass characteristics of the transmit circuit.

In embodiments of the invention, the present invention is directed to a contact hearing system including: a transmit circuit including a transmit coil positioned in an ear tip, the transmit circuit having a first passband, wherein the transmit circuit is tuned such that a center of the first passband is set at a first frequency; and a receive circuit including a receive coil positioned on a contact hearing device, the receive circuit having a second passband, wherein the receive circuit is tuned such that a center of the second passband differs from the center of the first passband.

In embodiments of the invention, the present invention is directed to a contact hearing system including: a transmit circuit including a transmit coil positioned in an ear tip, the transmit circuit having a first bandpass characteristic, wherein the transmit circuit is tuned such that a center of the first bandpass characteristic is set at a first frequency; a receive circuit including a receive coil positioned on a contact hearing device, the receive circuit having a second bandpass characteristic, wherein the receive circuit is tuned such that a center of the second bandpass characteristic differs from the center of the first bandpass characteristic; and wherein the receive circuit is tuned such that the center of the second bandpass characteristic is tuned to a frequency which is lower than the first frequency. In embodiments of the invention, the receive circuit is tuned such that the center of the second bandpass characteristic is tuned to a frequency below a transmit carrier frequency. In embodiments of the invention, the receive circuit is tuned such that the center of the second bandpass characteristic is tuned to a frequency within 5 percent of the carrier frequency. In embodiments of the invention, the receive circuit is tuned such that the center of the second bandpass characteristic is tuned to a frequency within 10 percent of the carrier frequency. In embodiments of the invention, the receive circuit is tuned such that the center of the second bandpass characteristic is tuned to a frequency which is within the bandpass characteristics of the transmit circuit.

In embodiments of the invention, the present invention is directed to a method of tuning a transmit circuit and a receive circuit, wherein the transmit and receive circuit form components of a contact hearing system, the transmit circuit having a bandpass characteristic and the receive circuit having a bandpass characteristic, the method including the steps of: tuning the bandpass characteristics of the transmit circuit such that a center of the transmit bandpass characteristic is set to a first frequency; and tuning the bandpass characteristics of the receive circuit such that a center of the receive bandpass characteristic is set to a second frequency, the second frequency differing from the first frequency. In embodiments of the invention, second frequency is higher than the first frequency. In embodiments of the invention, the first frequency is the transmit carrier frequency. In embodiments of the invention, the first frequency is approximately 2.56 MHz. In embodiments of the invention, the transmit circuit includes a transmit coil wound on a ferrite core, the transmit coil and ferrite core being positioned in an ear tip. In embodiments of the invention, the receive circuit includes a receive coil positioned on a contact hearing device. In embodiments of the invention, the transmit circuit and the receive circuit are adapted to be positioned in the ear canal of a user. In embodiments of the invention, the first frequency is selected to be less than 10% lower than the second frequency. In embodiments of the invention, the first frequency is selected to be less than 5 percent lower than the first frequency. In embodiments of the invention, the second frequency is within the bandpass characteristics of the transmit circuit. In embodiments of the invention, the second frequency is selected such that, if passed through a filter having the bandpass characteristics of the transmit circuit it would be attenuated by less than six decibels. In embodiments of the invention, the second frequency is selected such that, if passed through a filter having the bandpass characteristics of the receive circuit it would be attenuated by less than three decibels.

In embodiments of the invention, the present invention is directed to a method of tuning a transmit circuit and a receive circuit, wherein the transmit and receive circuit form components of a contact hearing system, the transmit circuit having a passband and the receive circuit having a passband, the method including the steps of: tuning the passband of the transmit circuit such that a center of passband of the transmit circuit is set to a first frequency; and tuning the bandpass characteristics of the receive circuit such that a center of the passband of the receive circuit is set to a second frequency, the second frequency differing from the first frequency.

In embodiments of the invention, the present invention is directed to a method of tuning a transmit circuit and a receive circuit, wherein the transmit and receive circuit form components of a contact hearing system, the transmit circuit having a bandpass characteristic and the receive circuit having a bandpass characteristic, the method including the steps of: tuning the bandpass characteristics of the transmit circuit such that the center of the bandpass is set to a first frequency; and tuning the bandpass characteristics of the receive circuit such that the center of the bandpass is set to a second frequency, the second frequency differing from the first frequency wherein the second frequency is lower than the first frequency. In embodiments of the invention, the first frequency is a transmit carrier frequency. In embodiments of the invention, the transmit circuit includes a transmit coil wound on a ferrite core, the transmit coil and ferrite core being positioned in an ear tip. In embodiments of the invention, the receive circuit includes a receive coil positioned on a contact hearing device. In embodiments of the invention, the transmit circuit and the receive circuit are adapted to be positioned in an ear canal of a user. In embodiments of the invention, the first frequency is selected to be less than 10% lower than the second frequency. In embodiments of the invention, the first frequency is selected to be less than 5 percent lower than the first frequency. In embodiments of the invention, the second frequency is within the bandpass characteristics of the transmit circuit. In embodiments of the invention, the second frequency is selected such that, if passed through a filter having the bandpass characteristics of the transmit circuit it would be attenuated by less than six decibels. In embodiments of the invention, the second frequency is selected such that, if passed through a filter having the bandpass characteristics of the transmit circuit it would be attenuated by less than three decibels. In embodiments of the invention, the second frequency is selected such that, if passed through a filter having the bandpass characteristics of the transmit circuit it would be attenuated by between 20 and 25 decibels. In embodiments of the invention, the first frequency is within the bandpass characteristics of the receive circuit. In embodiments of the invention, the first frequency is selected such that, if passed through a filter having the bandpass characteristics of the receive circuit it would be attenuated by between 10 and 15 decibels. In embodiments of the invention: the second frequency is selected such that, if passed through a filter having the bandpass characteristics of the transmit circuit it would be attenuated by between 20 and 25 decibels; and the first frequency is selected such that, if passed through a filter having the bandpass characteristics of the receive circuit it would be attenuated by between 10 and 15 decibels.

In embodiments of the invention, signals may be transmitted between the ear tip and the contact hearing device using an amplitude modulated oscillating magnetic field with a 2.5 MHz carrier frequency. In embodiments of the invention, the digital audio signal generated by the audio processor may be mixed with a carrier at the desired coupling frequency. In embodiments of the invention, the coupling circuit including the transmit coil subsystem and the receive coil subsystem may act as a band pass filter and the resulting waveform is an AM modulated signal which may be detected by the diode circuit connected to the receive coil. In embodiments of the invention, driver circuit may be a type D (H Bridge) and the mixing may be accomplished using an AND or a NAND gate with the carrier and the delta sigma digital modulation signal (the output of the delta sigma modulator, which may be a digital stream representative of an audio signal). In embodiments of the invention, the two legs of the H Bridge may be driven 180 degrees out of phase. In embodiments of the invention, the second leg may be driven by just the inverted (with respect to the other leg) carrier signal, allowing independent control of an additional carrier signal. This additional carrier may be used to overcome distortion caused by the non-linear current-voltage relationship of the diodes near the forward voltage Vfwithout sacrificing the dynamic range of the delta sigma modulator. The carrier leg voltage source can be independently controlled to adjust the amount of additional carrier inserted. In embodiments of the invention, the modulation may be FM or Frequency Modulation.

FIGS.28,49, and50are an illustrations of a circuit that uses a delta sigma modulator (DSM) signal input to modulate a carrier signal in a standard H-Bridge configuration. In embodiments of the invention, each side is driven 180 degrees out of phase with respect to each other. InFIGS.28,49, and50, the H-Bridge circuit may comprise one or more AND/NAND circuits1086, in combination with switches1088,1090,1092and1094. The output of the H-Bridge may be supplied to transmit coil290to provide an AM signal field which may transmitted to a receive coil130by, for example, inductively coupling the output of transmit coil290to receive coil130. In embodiments of the invention, illustrated inFIGS.49and50, one side of the H-Bridge may be coupled to transmit coil290through a capacitor C1Modulation is accomplished using the multiplicative property of the AND/NAND function.FIGS.28,49, and50are illustrations of a circuit according to the present invention wherein the DSM input is the delta sigma digital modulation signal. In embodiments of the invention, the output of the delta-sigma modulator is a signal representative of the sound received by the processor which is to be transmitted to the contact hearing device by amplitude modulation (AM) of the carrier. InFIGS.28,49, and50, the carrier may be a clock signal. InFIGS.28,49, and50, the carrier clock signal may be twice the DSM rate.FIGS.28,49and50, the carrier may be a digital clock signal representative of the carrier frequency, for example, 2.5 MHz. In embodiments of the invention, switches S1-S4may be solid state/digital switches, such as, FET transistors. In embodiments of the invention, S1-S4may form an H Bridge input to a resonant circuit (capacitor C1and inductor L1). In embodiments of the invention, the AM output signal may be formed by filtering the differential digital signal using a resonator. L1may be the transmit coil290. In the embodiment of the invention illustrated inFIGS.28and50, the input to a first side of the H Bridge is the NAND output of the AND/NAND gate circuit which has as its inputs the DSM signal and the Carrier signal. In the embodiment of the invention illustrated inFIG.49, the input to a first side of the H Bridge is the NAND output of the AND/NAND gate circuit which has as its inputs the DSM signal and the Carrier signal while the input to a second side of the H Bridge is the AND output of the AND/NAND gate circuit which has as its inputs the DSM signal and the Carrier signal. In embodiments of the invention, V1supply voltage controls the amount of modulated signal power transmitted. In embodiments of the invention, V2supply controls the additional carrier power. In embodiments of the invention, the AND/NAND gate(s) serves as the mixer, multiplying the modulation signal and the carrier, creating an AM modulation of the carrier.

FIGS.29and51are system models of a system according to the present invention, including transmission and receive tank circuits and a detector circuit. In embodiments of the invention, key components (e.g. the AND and NAND function along with the synchronization of the Pulse Density Modulation (PDM) with the clock) may be implemented using a Field Programmable Gate Array (FPGA). Further, the low capacitance FPGA output driver (for example, an iCE40 Output Driver from Lattice Semiconductor) may be used to create the H-Bridge. In embodiments of the invention, time skews and clock jitter can be kept at a minimum by re-clocking the outputs after the logic and just prior to the output driver. In embodiments of the invention, the circuit illustrated inFIGS.29and51may include discrete components to model the parasitic elements in the primary component. For example R2, R3and C2may be the parasitic resistance and capacitance in L1.

FIG.30illustrates the time domain waveform when the added carrier clock is the same size as the delta sigma signal mixed with the carrier clock.

FIG.31illustrates the resulting waveform with a 95% delta sigma with the added clock. Note that this is an AM signal with a modulation index of less than 50%. The embodiment illustrated inFIG.31may result in a lower distortion when using a simple diode detector while leaving the full dynamic range of the delta sigma modulator.

Several alternative methods of generating additional carrier exist. In embodiments of the invention, the signal could be generated using conventional analog means (mixer) then sum in additional carrier. In embodiments of the invention, the signal may be generated by digitally generating the desired waveform (including the added carrier) then using a high speed DAC (Digital to Analog converter. In embodiments of the invention, the mixing could also be performed by modulating the supply voltage to the H Bridge. In embodiments of the invention, this method could also be used to make a very simple cost effective AM modulator and by reversing the phase of the added carrier, suppressing the carrier double sideband suppressed carrier DSBSC. For standard AM the second leg of the H Bridge would be inverted from the first.

In one embodiment, the present invention is directed to a contact hearing system including: an ear tip including a transmit coil, wherein the transmit coil is connected to an audio processor, including an H Bridge circuit; a first input to the H Bridge circuit including an AND circuit wherein a first input to the AND circuit includes a carrier signal and a second input to the AND circuit includes an output of a delta sigma modulation circuit, wherein the delta sigma modulation circuit is a component of the audio processor; and a second input to the H Bridge circuit including an NAND circuit wherein a first input to the NAND circuit includes a carrier signal and a second input to the NAND circuit includes an output of the delta sigma modulation circuit. In embodiments of the invention, an output of a first side of the H Bridge circuit is connected to a first side of the transmit coil and an output of a second side of the H Bridge circuit is connected to a second side of the transmit coil. In embodiments of the invention, a capacitor is connected between at least one output of the H Bridge circuit and the transmit coil. In embodiments of the invention, the transmit coil is inductively coupled to a receive coil. In embodiments of the invention, the receive coil is positioned on a contact hearing device. In embodiments of the invention, the contact hearing device includes a diode detector connected to an output of the receive coil.

In one embodiment, the present invention is directed to a method of transmitting signals between a transmitter and receiver in an inductively coupled contact hearing system, the method including the steps of: mixing an output of a delta sigma modulation circuit with a carrier signal using an AND gate; providing an output of the AND gate to a first input of an H Bridge circuit; mixing the output of the delta sigma modulation circuit with the carrier signal using an NAND gate; providing an output of the NAND gate to a second input of the H Bridge circuit; providing an output of a first side of the H Bridge circuit to a first side of a transmit coil; and providing an output of a second side of the H Bridge circuit to a second side of the transmit coil. In embodiments of a method according to the present invention the method further including the steps of: receiving a signal generated by the transmit coil at a receive coil; passing the received signal through a diode detector. In embodiments of a method according to the present invention the method further including the step of: passing the output of the diode detector to a balanced armature transducer. In embodiments of the invention, the carrier is AM modulated. In embodiments of the invention, the diode detector demodulates the AM modulated carrier.

In one embodiment, the present invention is directed to a contact hearing system including: an ear tip including a transmit coil, wherein the transmit coil is connected to an audio processor, including an H Bridge circuit, wherein the transmit coil is connected to the output of the H Bridge circuit; a first input to the H Bridge circuit including an AND circuit wherein a first input to the AND circuit includes a carrier signal and a second input to the AND circuit includes an output of a delta sigma modulation circuit, wherein the delta sigma modulation circuit is a component of the audio processor; and a second input to the H Bridge circuit including the carrier signal. In embodiments of the invention, the second input is an inverted carrier signal. In embodiments of the invention, the transmit coil is inductively coupled to a receive coil. In embodiments of the invention, the receive coil is positioned on a contact hearing device. In embodiments of the invention, the contact hearing device includes a diode detector connected to an output of the receive coil.

In one embodiment, the present invention is directed to a method of transmitting signals between a transmitter and receiver in an inductively coupled contact hearing system, the method including the steps of: mixing the output of a delta sigma modulation circuit with a carrier signal using an AND gate; providing an output of the AND gate to a first input of an H Bridge circuit; providing a carrier signal to a second input of an H Bridge circuit; providing an output of a first side of the H Bridge circuit to a first side of a transmit coil; and providing an output of a second side of the H Bridge circuit to a second side of a transmit coil. In a method according to the present invention the method further including the steps of: receiving a signal generated by the transmit coil at a receive coil; passing the received signal through a diode detector. In a method according to the present invention the method further including the steps of: passing an output of the diode detector to a balanced armature transducer. In embodiments of the invention, the carrier is AM modulated. In embodiments of the invention, the diode detector demodulates the AM modulated carrier signal.

As described earlier, a Villard, 1-diode demodulator, such as, for example the circuit illustrated inFIG.36may be used as a demodulator circuit in embodiments of the present invention. In the circuit illustrated inFIG.36, receive coil130has an inductance L-Rx, which forms a tank resonator when used in combination with resonance capacitor977, having a tuning capacitance C-tune, which may be modified by the combined capacitances of the remaining circuit components, including AC filter capacitor975(which may be a series capacitor), Schottky diode1062and load1006(which may be, for example, a microactuator). In embodiments of the invention, resonance capacitor977may have a capacitance C-tune which is composed of 3 0201-size capacitors that are chosen to make the tank circuit resonate near or at the carrier frequency of approximately 2.5 MHz. In embodiments of the invention, the carrier frequency may be approximately 2.560 MHz. C-tune, in combination with the other components and, in particular, the Villard 1-diode demodulator may be chosen to provide a high output while minimizing intermodulation distortion (IMD).

In the embodiment of the invention, illustrated inFIG.36, a signal received by contact hearing device112and, on a negative half cycle of the carrier voltage, charge enters motor node1066through first diode1062, which may be, for example, a Schottky diode. On the subsequent positive half-cycle of the carrier, AC filter capacitor975and first diode1062holds this charge on motor node1066while displacement current travels through AC filter capacitor975into motor node1066. This sequence results in a voltage doubling at motor node1066on each carrier cycle. While acting as an efficient demodulator, a Villard circuit of the kind described may result in large voltage peaks at motor node1066, which large peaks may result in distortion, such as intermodulation distortion.

In the embodiment of the invention, illustrated inFIGS.37,47and48a Greinacher circuit may be used to demodulate a signal received by contact hearing device112. In embodiments of the invention, the Greinacher circuit may be a Villard circuit followed by a peak detector, wherein the peak detector may comprise a second diode1070(which may in some embodiments of the invention, be a Schottky diode) and a smoothing capacitor1068. The extra diode and capacitor act to smooth out the sharp voltage peaks on the Villard output. In a contact hearing device according to the present invention, smoothing capacitor1068may be used to present a more consistent output to load1006. In embodiments of the invention, smoothing capacitor1068may form a tank circuit with load1006wherein the presence of the tank circuit boosts the output of contact hearing device at frequencies around 10 kHz. In embodiments of the invention, smoothing capacitor1068may form a tank circuit with load1006wherein the presence of the tank circuit boosts the output of contact hearing device at the high end of the range of frequencies of interest (e.g. around 10 kHz). In embodiments of the invention, smoothing capacitor1068may form a tank circuit with load1006wherein the presence of the tank circuit boosts the output of contact hearing device at frequencies around 10 kHz, thereby ensuring that the output of contact hearing device112is substantially level across the range of frequencies of interest (e.g. from 100 Hz to 10,000 Hz) and does not fall off as the frequency approaches the higher end of the band. In embodiments of the invention, the circuit illustrated inFIG.37may be used to both minimize intermodulation distortion and maintain the output of contact hearing device112up to a frequency of approximately 10,000 Hz. In the embodiment ofFIG.47the Greinacher (2-diode) circuit includes an output filter. In the embodiment ofFIG.48the Greinacher (2-diode) circuit includes an LC output filter.

FIGS.47and48are illustrations of circuits used to implement a Greinacher demodulator with filter according to the present invention. In embodiments of the invention, the filter is intended to prevent (reduce) the carrier RF reaching the load (motor). In embodiments of the invention, the filter implementation is preferably low-pass, allowing the audio signals to pass with minimal attenuation up to 10 kHz while reducing/blocking the RF at 2.56 MHz or any carrier frequency. In embodiments of the invention, intermodulation distortion (IMD) is improved (around 5 dB) with two types of low-pass filters in this position. In embodiments of the invention, IMD may be improved by the addition of a filter to the Greinacher demodulator. In embodiments of the invention, the presence of the filter may reduce the amount of RF voltage on diode output node1067which reaching motor node1066, which will reduce the reflected RF from the motor from reaching the diodes (especially D2at diode output node1067) and mixing with the original signal. Mixing of signals in the diode, because of the non-linear I-V curve, results in distortion and may be the main contribution to IMD.

In embodiments of the invention, Villard (single diode) demodulation circuits may be used to increase the efficiency of the contact hearing device as they use a single diode which is only turned on for one half cycle. Unfortunately, Villard demodulation circuits produce larger spikes as they also act as voltage doublers. In demodulation circuits of this kind, the number of diodes in the circuit dictates its efficiency (in part) as the power needed to turn on a diode is not usable in signal transfer and is, therefore, lost. Greinacher (two diode) demodulation circuits have advantages over Villard demodulation circuits because the second diode of the Greinacher circuit in combination with smoothing capacitor1068smooths out the voltage and current spikes of the Villard, thus ensuring a smother demodulated signal and potentially reducing distortion. In addition, the Greinacher circuit is beneficial because it smooths out the response of the system across the frequency band of interest (in this case between approximately 100 Hz and 10,000 Hz such that the output of the demodulator is substantially the same across that range.

In embodiments of the invention, the present invention is directed to a contact hearing system including: a transmit coil positioned in an ear tip wherein the transmit coil includes an electrical coil wound on a ferrite core; a receive coil positioned on a contact hearing device wherein the receive coil includes an electrical coil without a core; a load connected to the receive coil; and a demodulation circuit connected to the receive coil and the load wherein the demodulation circuit includes a voltage doubler and a peak detector. In embodiments of the invention, the demodulation circuit is connected to the load at a motor node. In embodiments of the invention, a tuning capacitor is connected across the receive coil. In embodiments of the invention, the voltage doubler includes a series capacitor connected to a first diode. In embodiments of the invention, the series capacitor is connected between a first side of the receive coil and a cathode of the first diode. In embodiments of the invention, the cathode of the first diode is connected to a second side of the receive coil. In embodiments of the invention, the peak detector is connected between an output of the voltage doubler and the load. In embodiments of the invention, the peak detector includes a second diode and a smoothing capacitor. In embodiments of the invention, an anode of the second diode is connected to the voltage doubler. In embodiments of the invention, a cathode of the first diode is connected to an anode of the second diode. In embodiments of the invention, a cathode of the second diode is connected to a first side of the smoothing capacitor. In embodiments of the invention, the cathode of the second diode and the first side of the smoothing capacitor is connected to a first side of the load. In embodiments of the invention, a second side of the load is connected to a second side of the smoothing capacitor. In embodiments of the invention, the first diode is a Schottky diode. In embodiments of the invention, the second diode is a Schottky diode. In embodiments of the invention, the load is a microactuator. In embodiments of the invention, the load is a balanced armature microactuator.

FIG.38is a side view of a transmit coil for use in an ear tip according to the present invention.FIG.39is a top view of a transmit coil for use in an ear tip according to the present invention.FIG.40is a side perspective view of a transmit coil for use in an ear tip according to the present invention. In the embodiments of the invention, illustrated inFIGS.38-40, transmit coil290includes coil winding316which is wrapped around ferrite core318, which, in the embodiments ofFIGS.38-40may be a solid core with no acoustic vent. Transmit coil290may further include transmit electronics342.

FIG.41is an end view of an ear tip according to the present invention.FIG.42is an end view of an ear tip according to the present invention.FIG.43is a side view of an ear tip assembly according to the present invention. In the embodiments of the invention, illustrated inFIGS.41-43, ear tip120includes transmit coil290and acoustic vent338. Transmit coil290may include coil winding316and ferrite core316. In embodiments of the invention, ferrite core316may be constructed of a ferrite material or of any magnetic material. In embodiments of the invention, a distal end of ferrite core316may extend beyond a distal end of coil winding316.

In embodiments of the invention described and claimed herein, the text may refer to a “medial” or a “lateral” end or side of a device or component. In embodiments of the invention described and claimed herein, the text may refer to a “distal” or a “proximal” end or side of a device or component. In embodiments of the invention, “medial” and “distal” may refer to the side or end of the device or component which is farthest from the outside of the user's body (e.g. at the end of the ear canal where the tympanic membrane is found. In embodiments of the invention, “lateral” and “proximal” may refer to the side or end of the device or component which is closest to the outside of the user's body (e.g. at the open end of the ear canal where the pinna is found).

While the preferred embodiments of the devices and methods have been described in reference to the environment in which they were developed, they are merely illustrative of the principles of the present inventive concepts. Modification or combinations of the above-described assemblies, other embodiments, configurations, and methods for carrying out the invention, and variations of aspects of the invention that are obvious to those of skill in the art are intended to be within the scope of the claims. In addition, where this application has listed the steps of a method or procedure in a specific order, it may be possible, or even expedient in certain circumstances, to change the order in which some steps are performed, and it is intended that the particular steps of the method or procedure claim set forth herebelow not be construed as being order-specific unless such order specificity is expressly stated in the claim.

DEFINITIONS

Audio Processor—A system for receiving and processing audio signals. In embodiments of the invention, audio processors may include one or more microphones adapted to receive audio which reaches the user's ear. In embodiments of the invention, the audio processor may include one or more components for processing the received sound. In embodiments of the invention, the audio processor may include digital signal processing electronics and software which are adapted to process the received sound. In embodiments of the invention, processing of the received sound may include amplification of the received sound. In embodiments of the invention, the output of the audio processor may be a signal suitable for driving an inductive coil located in an ear tip. Audio processors may also be referred to as behind the ear units or BTEs.

Contact Hearing System—A system including a contact hearing device, an ear tip and an audio processor. In embodiments of the invention, contact hearing systems may also include an external communication device. In embodiments of the invention, power and/or data may be transmitted between an ear tip and a contact hearing device using inductive coupling.

Contact Hearing Device—A tiny actuator connected to a customized ring-shaped support platform that floats on the ear canal around the eardrum, where the actuator directly vibrates the eardrum causing energy to be transmitted through the middle and inner ears to stimulate the brain and produce the perception of sound. In embodiments of the invention, the contact hearing device may comprise a coil, a microactuator connected to the coil and a support structure supporting the coil and microactuator. The contact hearing device may also be referred to as a Tympanic Contact Actuator (TCA), a Tympanic Lens or a Tympanic Membrane Transducer (TMT).

Ear Tip—A structure designed to be placed into and reside in the ear canal of a user, where the structure is adapted to receive signals from an audio processor and transmit signals to the user's tympanic membrane or to a device positioned on or near the user's tympanic membrane (such as, for example, a contact hearing device). In embodiments of the invention, the signal may be transmitted using inductive coupling, using, for example, a coil connected to the Ear Tip.

Inductively Driven Hearing Aid System—a contact hearing system wherein signals are transmitted from an ear tip to a contact hearing device using inductive coupling. In an inductively driven hearing system, magnetic waves may be used to transmit information, power or both information and power from the ear tip to the contact hearing device.

Mag Tip—an ear tip adapted for use in an inductively driven hearing aid system. In embodiments of the invention, the mag tip may include an inductive transmit coil.

REFERENCE NUMBERS

NumberElement110Contact Hearing System112Contact Hearing Device114Grasping Tab116Demodulator118Sulcus Platform120Ear Tip/Mag Tip122Adhesive124Drive Post126Oil Layer128Charging Status LEDs130Receive coil132Audio Processor134AC Adapter Port136Charging Station138Charging Slots140Microactuator141Support Structure142Electromagnetic waves144Springs220Umbo Lens250Taper Tube260Cable290Transmit Coil310External Microphone312Transmit Electronics314Volume/Control Switch316Coil Winding318Ferrite Core312Canal Microphone320Analog to Digital Converter324External Communication and Control Device330Digital Signal Processor332Central Chamber334Mounting Recess336Secondary Acoustic Vent338Acoustic Vent340Acoustic Input (Audible Sound)342Transmit Electronics700Upstream Signal702Upstream Data710Downstream Signal712Downstream Data720Interface730Clock Recovery Circuit740Data Recovery Circuit750Energy Harvesting Circuit760Power management Circuit770Voltage Regulator780Driver790Data Processor Encoder800Data/Sensor Interface802External Antenna804Bluetooth Circuit806Battery808Power Conversion Circuit810Microphones812Charging Antenna814Wireless Charging Circuit816Interface Circuit818Power/Data Link822Interface Circuit823Biological Sensors824Energy Harvesting and Data Recovery Circuit826Energy Storage Circuitry828Power Management Circuitry831Matching Network832Data/Signal Processing Circuitry834Microcontroler836Driver838Microactuator840Digital Signal Processors (shown as MA in FIG. 7appears to be wrong)842Cloud Based Computer844Cell Phone846Data Acquisition Circuit848MPPT Control Circuit852Current Sensor854Capacitor863Voltage Meter865Rectifier and Converter Circuit869Storage Device872Parasitic Capacitance882Load972Capacitor974Diode975AC Filter Capacitor976Input Circuit977Resonance Capacitor (Tuning Capacitor)978Output Circuit980Drive Coil L1982Load Coil L4984Resonant Transmit Coil L2986Resonant Receive Coil L3988Drive (Transmit) Circuit990Load (Receive) Circuit992Transmit Resonant Circuit994Receive Resonant Circuit996Signal Source998Resonant Transmit Capacitor C11000Resonant Receive Capacitor C21002Voltage Detector1004Rectifier Circuit1006Load1008Receive Inductor Lrx1010Receive Capacitor Cr11012Receive Capacitor Cr21014Receive Capacitor Cr31016Receive Capacitor Cr41018Diode D1 (Schottky)1020Diode D21022Diode D31024Diode D41026Smoothing Capacitor 10261028Motor1030Motor Resistor (Resistance)1032Motor Inductor (Inductance)1034Diode Bridge1036Transmitter1038Current Source1040Output Capacitor C01042Output Coil L11044Voltage Source1046Capacitive Transformer/Divider1048Resistor R11050Capacitor C011052Capacitor C021054Inductor L11056Parallel Drive Circuit1058Capacitor C71060Capacitor C11062First Diode1066Motor Node1067Diode Output Node1068Smoothing Capacitor1070Second Diode1072Receive Circuit Components1074Receive Circuit Board1076Adhesive1078Ferrite Disk(s)1080Receive Coil Windings1082Adhesive Plug1084Receive Circuit Assembly1086AND/NAND Gate1088Switch S11090Switch S21092Switch S31094Switch S4