US20060136017A1 - Apparatus and method for treating strial hearing loss - Google Patents
Apparatus and method for treating strial hearing loss Download PDFInfo
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- US20060136017A1 US20060136017A1 US10/780,544 US78054404A US2006136017A1 US 20060136017 A1 US20060136017 A1 US 20060136017A1 US 78054404 A US78054404 A US 78054404A US 2006136017 A1 US2006136017 A1 US 2006136017A1
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- electrode
- assembly
- current
- electrolytic current
- charge injection
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/0526—Head electrodes
- A61N1/0541—Cochlear electrodes
Definitions
- strial presbycusis As many as seven million Americans suffer from a form of hearing loss known as strial presbycusis, which is marked by a loss of hearing in all registers and, as the name indicates, is associated with the aging process.
- endocochlear potential This voltage difference, referred to as “endocochlear potential,” causes current to flow through the hair cells. Sound waves cause the hair cells to bend, thereby changing their electrical conductivity and the amount of current that flows through them. This process results in the electrical nerve impulses that are sent to the brain by the auditory nerve.
- strial presbycusis is the deterioration of the stria vascularis, a structure that extends along the basilar membrane and produces the ions that create the endocochlear potential.
- the loss of endocochlear potential appears to result in both an immediate decline in hearing acuity and a gradual deterioration of the structure of the scala media.
- One potential method of restoring the enodocochlear potential is to inject additional charge by means of an electrode. This is difficult, however, because it requires the production of a DC current within the body. The body's interstitial tissues tend to foul and eventually destroy any implanted electrode producing a DC current. Further, metal electrodes either dissolve or become plated with new material when they are driven with DC currents. Because of this, existing therapeutic devices which produce electrical currents within the body, including pacemakers and neural stimulation systems, are driven by charge balanced, biphasic electrical pulses.
- the present invention is an electrolytic current injection device comprising an electrode and an electrolytic current port.
- a control and rectification assembly is adapted to apply a biphasic pulse to said electrode, yet produce a pulsatile, unidirectional DC electrolytic current at said electrolytic current port.
- FIG. 1 is an illustration of an implantable charge injection assembly and driver, according to the present invention, shown implanted in the skull.
- FIG. 2 is an illustration of the implantable charge injection assembly and driver of FIG. 1 , shown in relation to the structure of the inner ear.
- FIG. 3 is an illustration of the implantable charge injection assembly of FIG. 1 , shown in greater detail.
- FIG. 4 is a greatly expanded illustration of an electrostatically actuated micro machined gate, in its closed state, as utilized in the present invention.
- FIG. 5 is a greatly expanded illustration of an electrostatically actuated micro machined gate in its open state, as utilized in the present invention.
- FIG. 6 is an illustration of an alternative embodiment of an implantable charge injection assembly, which includes membranes that controllably and selectively permit the passage of electrolytes.
- FIG. 7 is an illustration of an additional alternative embodiment of an implantable charge injection assembly, which uses pressure actuated MEMS switches.
- FIG. 8 is an illustration of an additional alternative embodiment of an implantable charge injection assembly, which has a rotatable electrode.
- FIG. 9 is an illustration of an additional alternative embodiment of an implantable charge injection assembly, which has two charge injection units.
- FIG. 10 is an illustration of an additional alternative embodiment of an implantable charge injection assembly, which has two charge injection units, but having a different construction from that of FIG. 9 .
- FIG. 11 is a timing diagram for the assembly of FIG. 9 , but that would apply equally as well (with analogous labeling) to the embodiment of FIG. 10 , and the embodiment of FIGS. 12 and 13 .
- FIG. 12 is a schematic diagram of an additional alternative embodiment of an implantable charge injection assembly, showing the assembly in a first state.
- FIG. 13 is a schematic diagram of an additional alternative embodiment of an implantable charge injection assembly, showing the assembly in a second state.
- an implantable charge injection assembly 10 is designed to be implanted in the human skull.
- a charge injection unit 12 will be placed so that it contacts the scala media of the subject.
- the structure of charge injection unit 12 includes an electrolytic fluid-filled liquid crystal polymer (LCP) housing 18 ( FIG. 3 ).
- the electrolytic fluid is an aqueous solution of — 0.17_M KCl to match the potassium concentration of human scala media tissue.
- a primary electrode 20 located in the housing 18 is made of conductive metal plated with IrOx and has a surface area sufficient to sustain a positive current pulse >5 microamperes for >1 second, e.g., of 1.6 ⁇ 10 9 ⁇ m 2 .
- Injection unit 12 includes a tip 22 that contacts the scala media and has an interior area that is less than one hundred thousandth that of electrode 20 , being between 100 ⁇ m and 10,000 ⁇ m. The length of the tip 22 is 0.2 mm to 0.5 mm.
- charge injection unit 12 determines the bulk of the DC resistance of unit 12 , which equals about 0.1 to 1 megohms, based on a resistivity of 36.7 ohm-cm for 0.17 M KCl at 37°C.
- Charge injection assembly 10 includes a tube 16 that extends from unit 12 to a refresh electrode 14 that is embedded in the temporalis muscle, or that may be located in a closed side chamber of the electrode assembly.
- Tube 16 has an inside diameter of 25 ⁇ m or more and is filled with KC1 liquid of appropriate molarity.
- An electrode driver and switch control assembly 28 controls a micro machined gate 30 assembly with flap 32 (FIGS. 3 4 and 5 ), which exposes electrode 20 to either tip 22 or refresh electrode 14 .
- assembly 28 drives electrode 20 to cause it to inject charge into the scala media by way of tip 12 .
- electrodes 20 and 14 will be driven so that electrolytic current flows into and thereby refreshes primary electrode 20 , analogous to half-wave rectification.
- the single bi-state gate could also be replaced by two separate single-state gates operating in opposite phase from one another.
- gate 30 is electrostatically actuated.
- Gate 30 is made by the photolithographic conductive structures on thin sheets of liquid crystal polymer (LCP) combined with the laser micromachining of a small flap 32 .
- the flap 32 is kept closed by maintaining a small opposite charge on electrodes placed on the surfaces of flap 32 .
- the facing electrodes are electrically separated by a surface dielectric.
- LCP material which is thermoplastic, material can be selectively adhered by spot “welding” using an IR laser, or selectively removed using a UV laser, allowing a variety of designs to be implemented.
- the gate is mechanically pre-biased to remain closed. The bias is then overcome electrostatically to actuate the gate.
- a pair of ion-selective membranes 36 and 38 that permit the flow of positive ions from electrode surface 20 in a direction toward the tip of the electrode 22 , while simultaneously allowing the flow of negative ions from electrode 14 and surrounding tissue.
- the gate is actuated with pressure.
- gate 30 is made with a flexible, insulating membrane that is moved with pressure to open and close the orifice in chamber 33 . To close the gate, the pressure above the membrane exceeds that in the chamber. To open the gate the pressure above the membrane is equal to or less than that in the chamber. If the pressure is equal, the elasticity of the membrane produces a restoring force that opens the gate, while if the pressure is less, the pressure differential opens the gate.
- a primary electrode 20 ′ is rotatable, so that a first face 62 can be refreshed while a second face 64 is actively injecting current into the scala media.
- Electrode 20 (or 20 ′) is capable of passing a current of 10 ⁇ A for a duration of 3-6 sec through tip 22 and into the scala media. Scientific investigation has indicated that during the 3-6 second refresh periods for electrode 20 , the potential across the basilar membrane will persist.
- an additional preferred embodiment of a charge injection assembly 90 permits a continuous injection of charge into the scala media, analogous to full-wave rectification. Patients that have a damaged scala media, which is less capable of storing charge, may prefer this embodiment.
- Assembly 90 includes a pair of charge injection units 106 and 108 , which are toggled in their active states by an electrode driver and switch control assembly 28 controlling ion selective membranes 36 and 38 to maintain a continuous charge injection.
- Units 106 and 108 include a pair of driving electrodes 120 and 122 respectively, and a pair of tips 124 and 126 respectively.
- One or more refresh electrodes 130 are used to maintain electrodes 120 and 122 , so that an injection of charge into the scala media can be continuously maintained, by switching between tips 124 and 126 .
- the duty factor of the charge injection is increased, but is still not continuous.
- an alternative embodiment of an assembly 104 is conceptually the same as assembly 90 except for that instead of ion selective membranes 36 and 38 a pair of MEMS switches 130 and 132 are used for alternately occluding unit 106 and 108 .
- the current driver and switch control assembly 28 are sized to drive a maximum current of 5-30 ⁇ A in either direction.
- the driver in which the resistance of unit 12 is 1 M ⁇ , the driver is designed to remain linear over a range of at least ⁇ 30 volts.
- the dimensions of unit 12 are altered so as to reduce the resistance of unit 12 .
- the voltage level of the fluid of the scala media is measured and used to regulate the amount of current injected. It is noted that a large peak voltage has the potential for causing damage to body tissue and should generally be avoided.
- FIG. 11 shows the logic of assemblies 90 , 104 and 210 (referring specifically to FIGS. 12 and 13 ), where i(t) is the current applied from the current generator, and the other graphs in the sketch of the logic show the positions of the MEMS switches.
- the current drive is discontinuous and that the time that the drive is applied during each half cycle is less than the total time of a half cycle.
- Current is delayed at the beginning of each half cycle to ensure that the MEMS gates are properly opened and closed before current flows through the system.
- Current is shut off prior to the end of each half cycle to ensure that no current will be driven during the time that the MEMS gates close.
- current is unidirectional (injected) into the scala media, it is not true DC, but is interrupted.
- FIGS. 12 and 13 show a charge injection assembly 210 designed to overcome the problem that is outlined in the paragraph above.
- the assembly 210 is modified to be fully closed and isolated from the tissue, save through a pair of valves 236 leading into the scala media.
- KC1 is confined to the assembly 210 and to the scala media, where it is found naturally.
- a third metallic electrode 230 is contained in the KCl-filled electrode assembly. That third electrode is connected by a metallic conductor 240 to a fourth electrode 250 , which is embedded in the sodium-rich tissues that are external to the scala media via a fourth.
- This design contains the potassium-rich solutions in tissues where potassium is the normally the dominant ion. It provides a return path for the two active electrodes 220 and 222 , by way of valves 238 .
- FIG. 12 shows the implementation of assembly 210 with current flowing from electrode 220 , via the scala media and external tissue, through the external electrode 230 and thence to the right-hand assembly electrode 222 , which is negatively charged.
- FIG. 13 reverses the process.
Abstract
An electrolytic current injection device comprising an electrode and an electrolytic current port. In addition a control and rectification assembly is adapted to apply a biphasic pulse to said electrode, yet produce a pulsatile, unidirectional DC electrolytic current at said electrolytic current port. In one preferred embodiment a set of micro machined switches and a refresh electrode are used to maintain the unidirectional DC electrolytic current over time.
Description
- This application is a divisional of Ser. No. 10/287,989 filed Nov. 5, 2002.
- The invention was made with government support under grant number R43DC005531-01 ZRG01. The government has certain rights in the invention.
- As many as seven million Americans suffer from a form of hearing loss known as strial presbycusis, which is marked by a loss of hearing in all registers and, as the name indicates, is associated with the aging process. In a healthy ear there is a voltage difference across the basilar membrane, the organ that hosts the hair cells. This voltage difference, referred to as “endocochlear potential,” causes current to flow through the hair cells. Sound waves cause the hair cells to bend, thereby changing their electrical conductivity and the amount of current that flows through them. This process results in the electrical nerve impulses that are sent to the brain by the auditory nerve.
- It appears that the most frequent immediate cause of strial presbycusis is the deterioration of the stria vascularis, a structure that extends along the basilar membrane and produces the ions that create the endocochlear potential. The loss of endocochlear potential appears to result in both an immediate decline in hearing acuity and a gradual deterioration of the structure of the scala media. One potential method of restoring the enodocochlear potential is to inject additional charge by means of an electrode. This is difficult, however, because it requires the production of a DC current within the body. The body's interstitial tissues tend to foul and eventually destroy any implanted electrode producing a DC current. Further, metal electrodes either dissolve or become plated with new material when they are driven with DC currents. Because of this, existing therapeutic devices which produce electrical currents within the body, including pacemakers and neural stimulation systems, are driven by charge balanced, biphasic electrical pulses.
- The present invention is an electrolytic current injection device comprising an electrode and an electrolytic current port. In addition a control and rectification assembly is adapted to apply a biphasic pulse to said electrode, yet produce a pulsatile, unidirectional DC electrolytic current at said electrolytic current port.
- The foregoing and other objectives, features and advantages of the invention will be more readily understood upon consideration of the following detailed description of the invention, taken in conjunction with the accompanying drawings.
-
FIG. 1 is an illustration of an implantable charge injection assembly and driver, according to the present invention, shown implanted in the skull. -
FIG. 2 is an illustration of the implantable charge injection assembly and driver ofFIG. 1 , shown in relation to the structure of the inner ear. -
FIG. 3 is an illustration of the implantable charge injection assembly ofFIG. 1 , shown in greater detail. -
FIG. 4 is a greatly expanded illustration of an electrostatically actuated micro machined gate, in its closed state, as utilized in the present invention. -
FIG. 5 is a greatly expanded illustration of an electrostatically actuated micro machined gate in its open state, as utilized in the present invention. -
FIG. 6 is an illustration of an alternative embodiment of an implantable charge injection assembly, which includes membranes that controllably and selectively permit the passage of electrolytes. -
FIG. 7 is an illustration of an additional alternative embodiment of an implantable charge injection assembly, which uses pressure actuated MEMS switches. -
FIG. 8 is an illustration of an additional alternative embodiment of an implantable charge injection assembly, which has a rotatable electrode. -
FIG. 9 is an illustration of an additional alternative embodiment of an implantable charge injection assembly, which has two charge injection units. -
FIG. 10 is an illustration of an additional alternative embodiment of an implantable charge injection assembly, which has two charge injection units, but having a different construction from that ofFIG. 9 . -
FIG. 11 is a timing diagram for the assembly ofFIG. 9 , but that would apply equally as well (with analogous labeling) to the embodiment ofFIG. 10 , and the embodiment ofFIGS. 12 and 13 . -
FIG. 12 is a schematic diagram of an additional alternative embodiment of an implantable charge injection assembly, showing the assembly in a first state. -
FIG. 13 is a schematic diagram of an additional alternative embodiment of an implantable charge injection assembly, showing the assembly in a second state. - Referring to
FIGS. 1 and 2 , an implantablecharge injection assembly 10 according to the present invention, is designed to be implanted in the human skull. Acharge injection unit 12 will be placed so that it contacts the scala media of the subject. In one preferred embodiment, the structure ofcharge injection unit 12 includes an electrolytic fluid-filled liquid crystal polymer (LCP) housing 18 (FIG. 3 ). The electrolytic fluid is an aqueous solution of —0.17_M KCl to match the potassium concentration of human scala media tissue. Referring toFIG. 3 , aprimary electrode 20 located in thehousing 18 is made of conductive metal plated with IrOx and has a surface area sufficient to sustain a positive current pulse >5 microamperes for >1 second, e.g., of 1.6×109 μm2.Injection unit 12 includes atip 22 that contacts the scala media and has an interior area that is less than one hundred thousandth that ofelectrode 20, being between 100 μm and 10,000 μm. The length of thetip 22 is 0.2 mm to 0.5 mm. - The dimensions of
charge injection unit 12 determine the bulk of the DC resistance ofunit 12, which equals about 0.1 to 1 megohms, based on a resistivity of 36.7 ohm-cm for 0.17 M KCl at 37°C. -
Charge injection assembly 10 includes atube 16 that extends fromunit 12 to arefresh electrode 14 that is embedded in the temporalis muscle, or that may be located in a closed side chamber of the electrode assembly. Tube 16 has an inside diameter of 25 μm or more and is filled with KC1 liquid of appropriate molarity. - An electrode driver and
switch control assembly 28 controls a micro machinedgate 30 assembly with flap 32 (FIGS. 3 4 and 5), which exposeselectrode 20 to eithertip 22 orrefresh electrode 14. When thegate assembly 30 is positioned to connectelectrode 20 totip 22,assembly 28 driveselectrode 20 to cause it to inject charge into the scala media by way oftip 12. When thegate assembly 30 is positioned to connectelectrode 20 to therefresh electrode 14,electrodes primary electrode 20, analogous to half-wave rectification. The single bi-state gate could also be replaced by two separate single-state gates operating in opposite phase from one another. - Referring to
FIGS. 4 and 5 , in onepreferred embodiment gate 30 is electrostatically actuated.Gate 30 is made by the photolithographic conductive structures on thin sheets of liquid crystal polymer (LCP) combined with the laser micromachining of asmall flap 32. Theflap 32 is kept closed by maintaining a small opposite charge on electrodes placed on the surfaces offlap 32. The facing electrodes are electrically separated by a surface dielectric. To open the switch, like polarity is applied to both electrodes. By utilizing LCP material, which is thermoplastic, material can be selectively adhered by spot “welding” using an IR laser, or selectively removed using a UV laser, allowing a variety of designs to be implemented. In an alternative approach, the gate is mechanically pre-biased to remain closed. The bias is then overcome electrostatically to actuate the gate. - Referring to
FIG. 6 , in an alternative preferred embodiment, a pair of ion-selective membranes electrode surface 20 in a direction toward the tip of theelectrode 22, while simultaneously allowing the flow of negative ions fromelectrode 14 and surrounding tissue. In another preferred embodiment the gate is actuated with pressure. Referring toFIG. 7 ,gate 30 is made with a flexible, insulating membrane that is moved with pressure to open and close the orifice inchamber 33. To close the gate, the pressure above the membrane exceeds that in the chamber. To open the gate the pressure above the membrane is equal to or less than that in the chamber. If the pressure is equal, the elasticity of the membrane produces a restoring force that opens the gate, while if the pressure is less, the pressure differential opens the gate. - In yet another preferred embodiment, shown in
FIG. 8 , aprimary electrode 20′ is rotatable, so that afirst face 62 can be refreshed while asecond face 64 is actively injecting current into the scala media. - Electrode 20 (or 20′) is capable of passing a current of 10 μA for a duration of 3-6 sec through
tip 22 and into the scala media. Scientific investigation has indicated that during the 3-6 second refresh periods forelectrode 20, the potential across the basilar membrane will persist. Referring toFIG. 9 , an additional preferred embodiment of acharge injection assembly 90 permits a continuous injection of charge into the scala media, analogous to full-wave rectification. Patients that have a damaged scala media, which is less capable of storing charge, may prefer this embodiment.Assembly 90 includes a pair ofcharge injection units control assembly 28 controlling ionselective membranes Units electrodes tips more refresh electrodes 130 are used to maintainelectrodes tips - Referring to
FIG. 10 , an alternative embodiment of anassembly 104 is conceptually the same asassembly 90 except for that instead of ionselective membranes 36 and 38 a pair of MEMS switches 130 and 132 are used for alternately occludingunit - For any of the above described embodiments, the current driver and switch
control assembly 28 are sized to drive a maximum current of 5-30 μA in either direction. In one preferred embodiment, in which the resistance ofunit 12 is 1 MΩ, the driver is designed to remain linear over a range of at least ±30 volts. In another preferred embodiment, the dimensions ofunit 12 are altered so as to reduce the resistance ofunit 12. In another preferred embodiment the voltage level of the fluid of the scala media is measured and used to regulate the amount of current injected. It is noted that a large peak voltage has the potential for causing damage to body tissue and should generally be avoided. -
FIG. 11 shows the logic ofassemblies FIGS. 12 and 13 ), where i(t) is the current applied from the current generator, and the other graphs in the sketch of the logic show the positions of the MEMS switches. Note that the current drive is discontinuous and that the time that the drive is applied during each half cycle is less than the total time of a half cycle. Current is delayed at the beginning of each half cycle to ensure that the MEMS gates are properly opened and closed before current flows through the system. Current is shut off prior to the end of each half cycle to ensure that no current will be driven during the time that the MEMS gates close. In summary, while current is unidirectional (injected) into the scala media, it is not true DC, but is interrupted. - One problem encountered with the use of the systems described above is that they may permit sodium ions from the body tissue outside the scala media to corrupt the scala media fluid, which is rich in potassium ions. Likewise, potassium ions from the scala media may migrate into and damage body tissue.
-
FIGS. 12 and 13 show acharge injection assembly 210 designed to overcome the problem that is outlined in the paragraph above. Theassembly 210 is modified to be fully closed and isolated from the tissue, save through a pair of valves 236 leading into the scala media. KC1 is confined to theassembly 210 and to the scala media, where it is found naturally. A thirdmetallic electrode 230 is contained in the KCl-filled electrode assembly. That third electrode is connected by ametallic conductor 240 to afourth electrode 250, which is embedded in the sodium-rich tissues that are external to the scala media via a fourth. This design contains the potassium-rich solutions in tissues where potassium is the normally the dominant ion. It provides a return path for the twoactive electrodes valves 238. -
FIG. 12 shows the implementation ofassembly 210 with current flowing fromelectrode 220, via the scala media and external tissue, through theexternal electrode 230 and thence to the right-hand assembly electrode 222, which is negatively charged.FIG. 13 reverses the process. - Since current is not driven with a 100% duty cycle, as is described in the text associated with
FIG. 11 , the absence of current for a portion of the time, permits theinternal electrode 230 andexternal electrode 250 to depolarize relative to each other. - The terms and expressions which have been employed in the foregoing specification are used as terms of description and not of limitation, and there is no intention, in the use of such terms and expressions, of excluding equivalents of the features shown and described or portions thereof, it being recognized that the scope of the invention is defined and limited only by the claims which follow.
Claims (1)
1. An electrolytic current injection device comprising:
(a) an electrode;
(b) an electrolytic current port; and
(c) a control and rectification assembly adapted to apply a biphasic pulse to said electrode, yet produce a pulsatile, unidirectional DC electrolytic current at said electrolytic current port.
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/780,544 US20060136017A1 (en) | 2002-11-05 | 2004-02-17 | Apparatus and method for treating strial hearing loss |
US10/918,237 US20060136010A1 (en) | 2002-11-05 | 2004-08-13 | Strial hearing loss treatment device having a sliding electrode |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/287,989 US6694190B1 (en) | 2002-11-05 | 2002-11-05 | Apparatus and method for treating strial hearing loss |
US10/780,544 US20060136017A1 (en) | 2002-11-05 | 2004-02-17 | Apparatus and method for treating strial hearing loss |
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US10/287,989 Division US6694190B1 (en) | 2002-11-05 | 2002-11-05 | Apparatus and method for treating strial hearing loss |
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US10/918,237 Continuation-In-Part US20060136010A1 (en) | 2002-11-05 | 2004-08-13 | Strial hearing loss treatment device having a sliding electrode |
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US20060136017A1 true US20060136017A1 (en) | 2006-06-22 |
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US10/287,989 Expired - Fee Related US6694190B1 (en) | 2002-11-05 | 2002-11-05 | Apparatus and method for treating strial hearing loss |
US10/780,544 Abandoned US20060136017A1 (en) | 2002-11-05 | 2004-02-17 | Apparatus and method for treating strial hearing loss |
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US10/287,989 Expired - Fee Related US6694190B1 (en) | 2002-11-05 | 2002-11-05 | Apparatus and method for treating strial hearing loss |
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US8463393B2 (en) * | 2006-06-22 | 2013-06-11 | Medtronic, Inc. | Implantable medical devices having a liquid crystal polymer housing |
US9242094B2 (en) | 2010-01-12 | 2016-01-26 | The Johns Hopkins University | Implantable vestibular prosthesis |
WO2011088130A2 (en) | 2010-01-12 | 2011-07-21 | The Johns Hopkins University | Implantable vestibular prosthesis |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6045528A (en) * | 1997-06-13 | 2000-04-04 | Intraear, Inc. | Inner ear fluid transfer and diagnostic system |
US6529778B2 (en) * | 1999-12-19 | 2003-03-04 | Impulse Dynamics N.V. | Fluid-phase electrode lead |
Family Cites Families (1)
Publication number | Priority date | Publication date | Assignee | Title |
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US3751605A (en) * | 1972-02-04 | 1973-08-07 | Beckman Instruments Inc | Method for inducing hearing |
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2002
- 2002-11-05 US US10/287,989 patent/US6694190B1/en not_active Expired - Fee Related
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2004
- 2004-02-17 US US10/780,544 patent/US20060136017A1/en not_active Abandoned
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6045528A (en) * | 1997-06-13 | 2000-04-04 | Intraear, Inc. | Inner ear fluid transfer and diagnostic system |
US6529778B2 (en) * | 1999-12-19 | 2003-03-04 | Impulse Dynamics N.V. | Fluid-phase electrode lead |
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