WO2003073959A2 - Capteur intraoculaire - Google Patents

Capteur intraoculaire Download PDF

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Publication number
WO2003073959A2
WO2003073959A2 PCT/IL2003/000163 IL0300163W WO03073959A2 WO 2003073959 A2 WO2003073959 A2 WO 2003073959A2 IL 0300163 W IL0300163 W IL 0300163W WO 03073959 A2 WO03073959 A2 WO 03073959A2
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WO
WIPO (PCT)
Prior art keywords
sensor
lens
electrically conducting
eye
passage
Prior art date
Application number
PCT/IL2003/000163
Other languages
English (en)
Other versions
WO2003073959A3 (fr
Inventor
Shay Kaplan
Original Assignee
Microsense Cardiovascular Systems 1996
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Microsense Cardiovascular Systems 1996 filed Critical Microsense Cardiovascular Systems 1996
Priority to AU2003214592A priority Critical patent/AU2003214592A1/en
Publication of WO2003073959A2 publication Critical patent/WO2003073959A2/fr
Publication of WO2003073959A3 publication Critical patent/WO2003073959A3/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/16—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for measuring intraocular pressure, e.g. tonometers

Definitions

  • the present invention relates to wireless pressure sensors and systems in general and to sensors and systems for intraocular pressure measurement in particular.
  • Intraocular pressure measurement in the eye may provide important medical data for diagnostic purposes or for follow-up of therapeutic and/or surgical eye treatment.
  • Passive sensors for implanting into the human body or for mounting at some inaccessible location within a machine) are known in the art. These sensors are typically electromagnetic, providing an electromagnetic signal when activated.
  • the prior art sensor systems typically comprise a sensor, disposed in the region in which the measurement is to be performed, and an activating and detecting system.
  • the sensor is typically an oscillating circuit whose oscillation frequency changes in response to the physical variable to be measured.
  • the oscillating circuit typically includes a capacitor and an inductor, one or more of which is built to vary in accordance with the physical variable being measured.
  • the oscillation frequency of the sensor circuit is a function of the physical variable.
  • Electromagnetic sensors and systems are described in the U.S. Patent 4,127,110 and in an article: Carter C. Collins, "Miniature Passive Pressure Transensor for Implanting in the Eye", IEEE Transactions on Bio-Medical Engineering, Vol. BME-14, No. 2, April 1967, both incorporated herein by reference in their entirety for all purposes.
  • the passive sensor is detectable within a range of approximately 10 times the diameter of its antenna (part of the oscillating circuit).
  • the use of implantable wireless intraocular sensors may pose problems.
  • the limited ocular space puts a limit on the size and volume of the sensor that may be practically implanted within an eye without impairment of a patient's vision.
  • one may not use sensors which are bellow a certain size or diameter because the above range limit (10 times the diameter of the antenna) may practically prevent detection of the desired signal.
  • an implantable passive intraocular pressure sensor includes a sealed housing having a passage therein for allowing light to pass through the passage.
  • the housing has walls forming a sealed chamber therebetween. At least one wall of the walls is a movable wall configured for moving in response to changes in the pressure outside the sensor.
  • the sensor also includes a passive electromagnetic resonant circuit. At least one portion of the resonant circuit is mechanically coupled to the at least one movable wall such that the resonance frequency of the resonant circuit varies as a function of the pressure outside the sensor.
  • the dimensions of the passage are configured to allow light to pass through the passage to reach the retina of an eye when the sensor is implanted within the eye.
  • the housing is selected from the group consisting of: a flat annular housing, a flat regular polygonal annular housing, an annular housing having a flat ellipsoidal cross-section and a non-symmetrical housing having an irregular shape.
  • the passage is selected from the group consisting of: a passage having a circular cross- section, a passage having a polygonal cross-section, a passage having an ellipsoidal cross-section, a passage having a regular polygonal cross-section and an irregularly shaped passage.
  • the sealed chamber surrounds the passage.
  • the resonant circuit includes an electrically conducting member having at least two electrically coupled electrically conducting portions, and the distance between the at least two portions varies as a function of the pressure outside the sensor.
  • At least one electrically conducting portion of the at least two electrically conducting portions is attached to the at least one movable wall.
  • the chamber includes a gas sealed therein.
  • the at least one movable wall is a flexible deformable wall. At least a portion of the deformable wall is configured to change its shape in response to changes in the pressure outside the sensor. Furthermore, in accordance with an embodiment of the present invention, the passage is an open passage.
  • the senor also includes at least one optical element attached to the housing and disposed within the passage.
  • the senor is a foldable sensor configured to be folded to facilitate insertion thereof into an eye.
  • the at least one optical element is selected from a lens, an optical filter, a light polarizing element, and combinations thereof.
  • the senor further includes at least one handling member attached to the housing or formed as a part thereof to facilitate handling or grasping the sensor.
  • the lens further includes an additional electrically conducting member attached to the lens and electrically coupled to the passive electromagnetic resonant circuit to form an extended resonant circuit.
  • the additional electrically conducting member is shaped as a spirally shaped layer of electrically conducting material attached to a surface of the lens.
  • the additional electrically conducting member is shaped as a spirally shaped layer of electrically conducting optically transparent material attached to a surface of the lens.
  • the electrically conducting optically transparent material comprises indium tin oxide.
  • the lens is an implantable contact lens configured to be placed adjacent to the natural lens of an eye, and the sensor is configured to be implanted within the anterior chamber of the eye to enable determining the pressure therein. Furthermore, in accordance with an embodiment of the present invention, the lens is configured to replace the natural lens of an eye, and the sensor is configured to be implanted within the posterior chamber of the eye to enable determining the pressure therein. Furthermore, in accordance with an embodiment of the present invention, the lens is configured to replace the natural lens of an eye in cataract surgery performed on a patient.
  • the housing of the sensor includes two opposing non-planar annular membranes.
  • Each membrane of the two membranes has an inner circumference and an outer circumference.
  • the two membranes are sealingly attached to each other along their inner circumference and outer circumference to form the sealed chamber between them.
  • At least one of the membranes is a flexible or deformable membrane.
  • the resonant circuit includes at least a first electrically conducting portion and a second electrically conducting portion.
  • the first portion is electrically coupled to the second portion.
  • the first electrically conducting portion is attached to a first membrane of the two membranes and the second electrically conducting portion is attached to the second membrane of the two membranes.
  • the distance between at least a part of the first portion and at least a part of the second portion varies as a function of the pressure outside the sensor.
  • At least one of the first portion and the second portion of the resonant circuit includes a spirallike layer of electrically conducting material attached to a surface of a membrane of the two membranes.
  • At least one of the first portion and the second portion of the resonant circuit includes a layer of electrically conducting material attached to a surface of a membrane of the two membranes.
  • the layer is shaped as an annular layer having a gap therein.
  • the first portion and the second portion of the resonant circuit are electrically coupled by an electrically conducting member.
  • the electrically conducting member is configured such that it does not substantially hinder the changing of the distance between the at least part of the first portion and at least a part of the second portion of the resonant circuit when the pressure outside the sensor changes.
  • the electrically conducting member is selected from an electrically conducting wire, an electrically conducting ribbon, an electrically insulated electrically conducting wire and an electrically insulated electrically conducting ribbon.
  • the first portion of the resonant circuit includes a first spiral-like layer of electrically conducting material attached to a surface of the first membrane
  • the second portion of the resonance circuit includes a second spiral-like layer of electrically conducting material attached to a surface of the second membrane.
  • the first spiral-like layer and the second spiral like layer are configured such that the windings of the first spiral-like layer oppose the windings of the second spiral-like layer.
  • the first spiral-like layer and the second spiral like layer are configured such that the windings of the first spiral-like layer are laterally offset with respect the windings of the second spiral-like layer.
  • the first spiral-like layer and the second spiral like layer are configured such that the windings of the first spiral-like layer are interdigitated with the windings of the second spiral-like layer.
  • the first portion of the resonant circuit includes a first spiral-like layer of electrically conducting material attached to a surface of the first membrane, and the second portion of the resonant circuit includes a second layer of electrically conducting material.
  • the second layer is shaped as a single loop.
  • the second layer is attached to a surface of the second membrane.
  • the second layer is shaped as an electrically conducting single loop selected from a closed single loop and an open single loop having a gap therein.
  • the senor further includes at least one handling member attached to the housing or formed as a part thereof to facilitate handling or grasping of the sensor.
  • At least part of the housing includes at least one biocompatible material.
  • the passage has a circular cross-section having a diameter equal to or larger than two millimeters.
  • the passage has a circular cross-section having a diameter equal to or larger than three millimeters.
  • the biocompatible material is selected from the group consisting of polytetrafluoroethylene, polyethylene, polypropylene, Parylene® C, and combinations thereof.
  • At least part of the sensor includes at least one transparent material.
  • the transparent material is transparent to at least part of the portion of the electromagnetic spectrum visible to humans.
  • the senor is a foldable sensor configured to be folded to facilitate insertion thereof into an eye.
  • a method for implanting a sensor in an eye includes the step of Inserting into an eye a sensor including a sealed housing having a passage therein for allowing light to pass through the passage.
  • the housing has walls forming a sealed chamber therebetween. At least one wall of the walls is a movable wall configured for moving in response to changes in the pressure outside the sensor.
  • the sensor also includes a passive electromagnetic resonant circuit. At least one portion of the circuit is mechanically coupled to the at least one movable wall such that the resonance frequency of the resonant circuit varies as a function of the pressure outside the sensor.
  • the method also includes the step of positioning the sensor within the eye to allow part of the light entering the eye to reach the retina of the eye by passing through the passage.
  • the senor also includes at least one optical element attached to the housing and disposed within the passage, and the step of positioning includes positioning the sensor within the eye to allow part of the light entering the eye to reach the retina of the eye by passing through the at least one optical element.
  • the at least one optical element is an intraocular contact lens configured for implantation adjacent to the natural lens of an eye
  • the step of inserting includes inserting the sensor into the anterior chamber of the eye to dispose the intraocular contact lens adj acent the natural lens of the eye .
  • the at least one optical element is a lens configured for replacing the natural lens of an eye
  • the step of inserting includes inserting the sensor into the posterior chamber of the eye for replacing the natural lens of the eye following the surgical removal of the natural lens.
  • the optical element is selected from a lens, a multi-element lens, an optical filter, a light polarizing optical element and combinations thereof.
  • the lens includes an optically transparent lens body and a pressure sensor including a sealed housing having a passage therein.
  • the housing is attached to the lens body.
  • the lens body is disposed within the passage.
  • the housmg has walls forming a sealed chamber therebetween. At least one wall of the walls is a movable wall configured for moving in response to changes in the pressure outside the sensor.
  • the sensor also includes a passive electromagnetic resonant circuit. At least one portion of the circuit is mechanically coupled to at least one movable wall such that the resonance frequency of the resonant circuit varies as a function of the pressure outside the sensor.
  • the lens body and the sensor are foldable.
  • the passage has a circular cross-section having a diameter equal to or larger than three millimeters.
  • the lens body is attached to the housing of the sensor by a spacer member.
  • the spacer member is an annular spacer member.
  • the composite lens further includes one or more handling members for facilitating the handling or grasping of the composite lens.
  • the one or more handling members are attached to the housing or are formed as part of the housing.
  • the lens body is an implantable contact lens configured to be placed adjacent to the natural lens of an eye, and the sensor is configured to be implanted within the anterior chamber of the eye to enable determining the pressure therein.
  • the lens body is configured to replace the natural lens of an eye
  • the sensor is configured to be implanted within the posterior chamber of the eye to enable determining the pressure therein.
  • the lens body is configured to replace the natural lens of an eye in cataract surgery performed on a patient.
  • the lens further includes an additional electrically conducting member attached to the lens body and electrically coupled to the passive electromagnetic resonant circuit to form an extended resonant circuit.
  • the additional electrically conducting member is shaped as a spirally shaped layer of electrically conducting material attached to a surface of the lens body.
  • the additional electrically conducting member is shaped as a spirally shaped layer of electrically conducting optically transparent material attached to a surface of the lens body.
  • the electrically conducting optically transparent material comprises indium tin oxide.
  • Fig. 1A is a schematic cross-sectional view, illustrating a wireless intraocular implantable pressure sensor constructed in accordance with an embodiment of the present invention
  • Fig. IB is a schematic front view of the sensor of Fig. 1A as viewed from a direction indicated by the arrow 7 of Fig. 1 A;
  • Fig. 2 is a schematic diagram illustrating an electrical circuit equivalent of the resonant circuit 14 of Figs. 1A and IB;
  • Fig. 3 is a schematic, part cross-sectional view of an eye, illustrating a system for wireless intraocular pressure measurement including the wireless intraocular pressure sensor of Figs. 1A and IB implanted within the eye, an external antenna, and excitation and detection circuitry disposed outside the eye, in accordance with an embodiment of the present invention;
  • Figs. 4A and 4B are schematic cross-sectional views illustrating various different types of intraocular implantable pressure sensors having different configurations, in accordance with additional embodiments of the present invention
  • Fig. 4C is a schematic top view, illustrating in detail one of the membranes of the sensor of Fig. 4B;
  • Fig. 5 is a schematic cross-sectional views illustrating another type of intraocular implantable pressure sensor having a resonant -circuit including interdigitated electrical conducting members, in accordance with additional embodiments of the present invention.
  • Fig. 6 is a schematic cross sectional view illustrating an implantable intraocular lens including a wireless intraocular pressure sensor, in accordance with another embodiment of the present invention.
  • the present invention discloses implantable passive wireless electromagnetic pressure sensors and systems for determining intraocular pressure.
  • Fig. 1A is a schematic cross- sectional view, illustrating a wireless implantable pressure sensor constructed in accordance with an embodiment of the present invention.
  • Fig. IB is a front view of the sensor of Fig. 1A as viewed from a direction indicated by the arrow 7 of Fig. 1 A.
  • the implantable sensor 10 of Figs. 1A-1B may include a flat hollow annular housing 12 and a resonant circuit 14.
  • the annular housing 12 may include a first annular membrane 12A and a second annular membrane 12B.
  • the annular membranes 12A and 12B may be sealingly attached or glued or welded to each other at their outer circumference 12C and at their inner circumference 12D.
  • the sealed space 16 is a sealed chamber enclosed between the membranes 12A and 12B may includes a gas (not shown) or a gas mixture (not shown) therein.
  • the membranes 12A and 12B may be made from a suitable flexible biocompatible material, such as a suitable plastic material, or the like.
  • the membranes 12A and 12B may be made from Polytetrafluoroethylene (PTFE), or Polyethylene (PE), or Polypropylene (PP), Parylene® C, or the like.
  • PTFE Polytetrafluoroethylene
  • PE Polyethylene
  • PP Polypropylene
  • Parylene® C Parylene® C, or the like.
  • the membranes 12A and 12B may be made from an optically transparent (for light in the human visual range) biocompatible plastic material, but other non-transparent materials may also be used.
  • the annular housing 12 has an opening (a hole) 20 therein.
  • the opening 20 may be a circular opening disposed at the center of the housing 12 as illustrated in Figs. 1A and IB.
  • the opening 20 may, however, be differently shaped depending on the sensor's structure and shape.
  • the housing 12 may be shaped as a flat polygonal annular housing (not shown) with a polygonal opening (not shown) therein.
  • the housing 12 may be radially symmetrical with respect to the axis 22 (as illustrated in Fig. 1A), but may also be non symmetrically shaped (not shown).
  • the resonant circuit 14 includes a first electrically conducting spiral member 14A and a second electrically conducting spiral member 14B.
  • the first electrically conducting spiral member 14A may be attached to the first membrane 12 A, and the second electrically conducting spiral member 14B may be attached to the second membrane 12B.
  • the spiral electrically conducting members 14A and 14B are made from an electrically conducting material, such as, but not limited to, a metal, or any other suitable electrically conducting material.
  • the spiral members 14A and 14B may be formed by forming a layer of a conducting material or metal (such as, but not limited to, gold, silver, copper, or the like) on the internal surfaces 12E and 12F of the membranes 12A and 12B, respectively, followed by standard lithography methods, using various known techniques such as, photo-resist masking, etching, and the like, as is known in the art.
  • Optically transparent, electrically conducting materials such as, but not limited to, indium-tin oxide (ITO) or the like, may also be used for forming the members 14A and 14B of the resonant circuit 14, or of any other resonant circuits of the present invention disclosed in detail hereinafter.
  • ITO indium-tin oxide
  • spiral members 14A and 14B may also be used, such as, but not limited to, electroplating, chemical plating, sputtering, chemical vapor deposition, or the like, or any other suitable method known in the art for forming a layer of conducting material on a substrate.
  • Fig. IB the schematic front view of the sensor 10 illustrated in Fig. IB is drawn to show both of the spiral electrically conducting members 14A and 14B as may be seen through a transparent membrane 12A is made from a material.
  • the spiral electrically conducting members 14A and 14B of the resonant circuit 14 are typically not co-planar as may be seen in the cross-sectional view of Fig. 1 A.
  • the spiral electrically conducting member 14A is electrically connected to the spiral electrically conducting member 14B by a suitable electrical conductor 14C.
  • the electrical conductor 14C may be any suitable electrically conducting member, such as, but not limited to, an electrically conducting wire, or flat ribbon, or the like.
  • the electrical conductor 14C may be suitably electrically connected to the spiral electrically conducting members 14A and 14B by any suitable method known in the art, such as, but not limited to, welding methods, gluing with an electrically conducting glue (not shown), wire bonding methods, or the like.
  • the electrical conductor 14C may be an electrically insulated conductor, but may also be a non-insulated conductor.
  • the electrical conductor 14C is configured such that it does not substantially hinder, prevent, or restrict the movement of the membranes 12A and 12B when the pressure outside the sensor 14 changes. Different configurations of the electrical conductor 14C may be used. In accordance, with the embodiment illustrated in Fig. IB, the electrical conductor is suitably disposed within the space 16 of the housing 12 and may have some slack (by having a sufficient length) in order not to substantially hinder, prevent, or restrict the movement of the membranes 12A and 12B when the pressure outside the sensor 44 changes.
  • the electrical conductor 14C or at least parts thereof may be attached to, or disposed on, or deposited upon the external surfaces 12G and 12H of the membranes 12A and 12B, respectively (this embodiment is not shown in Fig. 1A).
  • the parts of the electrical conductor 14C which may be attached to the external surfaces 12G and 12H, may be properly electrically insulated by a suitable layer (not shown) or coating of a suitable biocompatible electrically insulating material, such as, but not limited to, Parylene® C, or the like. Care must be taken that the design, thickness and flexibility of the electrical conductor 14C (and of the insulation thereof, if used) are adapted to minimized or reduce substantial hindrance or restriction of the membranes 12A and 12B when the pressure outside the sensor 44 changes.
  • the electrically conducting spiral members 14A and 14B may be electrically insulated by coating them or the surfaces 12E and 12F with a suitable thin layer of an electrically insulating material.
  • the electrically conducting spiral members 14A and 14B may also be non insulated.
  • Fig. 2 is a schematic diagram illustrating an electrical circuit equivalent of the resonant circuit 14 of Figs. 1A and IB.
  • the circuit 31 includes a variable inductance LI, a variable capacitor C and a resistor R connected in series, hi the particular embodiment of the resonant circuit 14 of Figs. 1A and IB, the inductance LI schematically represents the variable lumped inductance of the resonant circuit 14 (which includes the spiral electrically conducting member 14A and the spiral electrically conducting member 14B), the capacitor C schematically represents the variable lumped capacitance of the entire resonant circuit 14, and the resistor R schematically represents the lumped resistance of the entire resonant circuit 14.
  • the resonance frequency of the circuit 31 depends on the values of LI, C and R.
  • the membranes 12A and 12B may deform, or may change their shape and/or their position relative to each other as is known in the art. If the pressure acting on the membranes 12A and 12B is greater than the pressure of the gas (or gases) within the sealed space 16, the membranes 12A and 12B may move closer to each other, and the distance between the spiral electrically conducting members 14A and 14B diminishes. If the pressure acting on the membranes 12A and 12B is smaller than the pressure of the gas (or gases) within the sealed space 16, the membranes 12A and 12B may move away from each other, and the distance between the spiral electrically conducting members 14A and 14B increases.
  • the membranes 12A and 12B may be concave membranes, when the membranes 12A and 12B deform or change their shape or move as a result of a pressure change, some parts of the membranes may move or change their shape differently than other parts of the same membranes.
  • the change of the distance between some of the windings of the electrically conducting members 14A and 14B may be different from the change of the distance between some other of the windings of the electrically conducting members 14A and 14B.
  • the changes in the distance between different parts of the members 14A and 14B in response to a change in the pressure acting on the sensor 10 may not be uniform.
  • the senor 10 is shown in a configuration in which both of the membranes 12A and 12B are flexible or deformable membranes, and both of the membranes may deform or change their shape or move with respect to each other, other embodiments of the present invention may include configurations in which only one of the membranes 12A and 12B is a flexible or deformable or movable membrane, while the remaining membrane is a substantially non-flexible membrane or a substantially non-deformable membrane which is sufficiently rigid and does not change its shape or deform in response to changes of the pressure outside the sensor.
  • the rigid membrane may be made rigid by fabricating it from a material or materials (or composite) having sufficient mechanical strength and greater rigidity than the material or materials (or composite) included in the more flexible or more deformable membrane of the sensor.
  • one membrane may be made rigid by fabricating it from a material or materials (or composite) having sufficient mechanical strength and greater rigidity than the material or materials (or composite) included in the more flexible or more deformable membrane of the sensor.
  • the senor may be made substantially rigid by increasing its thickness relative to the thickness of the second flexible or deformable membrane. It may further be possible to change both the thickness and the material composition of one of the membranes to increase its rigidity.
  • the membranes 12A and 12B of the sensor 10 are implemented as concave or convex membranes having a curvature, one or more of the membranes may be a planar or nearly planer membrane. Such nearly planar membranes are shown, for example, in Fig. 5 hereinbelow, but many other configurations may also be used including but not limited to generally annular sensors having a passage therethrough and having any combination of flat and/or concave/convex membranes with at least one membrane being a movable or deformable or flexible membrane.
  • one or more parts of the resonant circuit of the sensor of the present invention may be mechanically coupled to one or more of the movable or deformable walls of the sensor by any mechanical coupling means known in the art.
  • one or more of the spiral electrically conducting members 14A and 14B of the resonant circuit 14 of Figs. 1A and IB may be mechanically coupled to one the membranes 12 by a suitable coupling member (not shown) or coupling layer (not shown) as is known in the art.
  • the membrane 12A of the sensor 10 may be a substantially rigid membrane while the membrane 12B may be a flexible or deformable or movable membrane.
  • both of the membranes 12A and 12B may be configured as flat rigid annular membranes (not shown) each membrane having an opening therein (similar to the opening 20 of Figs.
  • the rigid flat membranes may be sealingly attached to each other by a suitably flexible connecting collar (such as by two accordion-like cylinders or crimped cylinders (not shown) suitably sealingly attached to the outer and inner circumference or rims of the rigid membranes.
  • R may typically be negligibly affected by changes in the distance between the spiral electrically conducting members 14A and 14B
  • the values of C (the variable lumped circuit capacitance of the resonant circuit 14 in the example illustrated in Figs. 1A and IB) and of LI (the variable lumped inductance of the resonant circuit 14,) may be substantially affected by changes in the distance between the spiral electrically conducting members 14A and 14B of the resonant circuit 14.
  • Changes in the pressure acting on the sensor 10 may thus lead to changes in the resonance frequency of the resonant circuit 14 of the sensor 10. These changes may be detected and the pressure acting on the sensor 10 may thus be determined, as is known in the art.
  • the methods for determining the pressure acting on sensors having resonant circuits (such as, for example, the resonant circuit 14 of the sensor 10) from the resonance frequency of the resonant circuit, are well known in the art, are not the subject matter of the present invention, and are therefore not described in detail hereinafter.
  • any of the methods for radio frequency (RF) excitation of a sensor's resonant circuit and for detection of the circuit's resonant frequency and determining the pressure therefrom may be used, as is known in the art.
  • Such methods may include, but are not limited to, passive load modulation methods (these methods may require suitable on-sensor circuitry for a wireless system to actively modulate a reflected load on a coupled primary inductor, as disclosed in detail by K.
  • FIG. 3 is a schematic part cross-sectional view of an eye, illustrating a system for wireless intraocular pressure measurement including the wireless intraocular pressure sensor of Figs. 1A and IB implanted within the eye, an external antenna, and excitation and detection circuitry disposed outside the eye, in accordance with an embodiment of the present invention.
  • the system 28 includes a sensor 10 which may be placed within the vitreous body 32 of an eye 30, and may be disposed behind the lens 34 of the eye 30.
  • the sensor 10 may be positioned such that light rays (such as, for example, the light rays 36 A and 36B) entering the eye and focused by the lens 34 may pass through the opening 20 of the sensor 10 and reach the retina 38 without being obstructed.
  • the axis 27 passes through the center point 37 of the annular sensor 10 and intersects the center of the fovea 39.
  • the diameter of the opening 20, and the distance between the sensor 10 and the lens 34 may be adapted such that no obstruction or rriinimal possible obstruction by the sensor 10 of light rays entering the eye and exiting from the lens 34 occurs, to ensure undisturbed or minimally disturbed visual function, respectively.
  • the system 28 further includes an external antenna 26 which may be disposed outside the eye 30.
  • the antenna 26 may include a coil 26A made from an electrically conducting material such as an insulated metal wire, made from copper, silver, or any other suitable electrically conducting material.
  • the external antenna 26 and the intraocularly disposed resonance circuit 14 of the sensor 10 may together form a loosely coupled transformer, as is known in the art.
  • the coil 26A may include one or more windings or loops of electrically conducting materials.
  • the coil 26 may or may not be an axi-symmetric coil and may also be a coil having an irregular shape.
  • the coil 26A is a substantially circular coil having an approximate center point 23.
  • Other coil forms may however also be used, including but not limited to,_coils having a regular polygonal structure, elliptically shaped coils, axially extended coils, irregularly shaped coils, or any other coil shapes and structures which are known in the art and suitable for use in loosely coupled transformer circuits.
  • the terminals 26B and 26C of the coil 26A may be suitably attached to excitation and detection circuitry 35, as is known in the art, for performing resonant peak passive telemetry, as is known in the art and disclosed in detail hereinabove, and to determine the intraocular pressure from the measured resonant peak, as is known in the art.
  • the advantage of the intraocular sensor 10 and of other intraocular implantable pressure sensors disclosed hereinafter over other implantable pressure sensors known in the art is that the opening in the disclosed sensors (such as, for example, the circular opening 20 of the sensor 10) and the sensor's positioning within the eye 30 allows the external antenna 26 to be disposed at a sufficiently large distance from the eye 30 to make practical and adequately accurate intraocular pressure measurements possible.
  • the approximate allowable separation between the antenna 26 and the sensor 10 is about 3 centimeters orTarger.
  • the distance between the center point 23 of the circular coil 26A and the center point 38 of the circular opening 20 may practically be 3 centimeters or even larger.
  • a suitable frame or member (not shown in Fig. 3) which may be worn by a patient.
  • Such a frame may be shaped similar to a pair of spectacles.
  • the antenna 26 may be suitably attached to a real pair of spectacles which are normally (or, optionally, post operatively) worn by the patient for vision correction, or for other purposes.
  • the antenna 26 may be suitably coupled to the excitation and detection circuitry 35 as is schematically illustrated in Fig. 3.
  • the excitation and detection circuitry 35 may include a miniaturized integrated circuit (IC) and a suitable power source (not shown), and may be suitably installed within, or suitably attached to, or suitably embedded within the frame or spectacles.
  • IC integrated circuit
  • a suitable power source not shown
  • one or more such excitation and detection circuitry 35 or parts thereof may be installed within, or suitably attached to, or suitably embedded within the handles of the spectacles or spectacles-like frame, or the part or parts of the spectacles or spectacles-like frame which are used to fix or attach the frame to the ears of the patient.
  • Other suitable methods for attaching or affixing the antennas 26 and/or the excitation and detection circuitry 35 to frames worn by the patient may ,however, be used, as is known in the art.
  • the excitation and detection circuitry 35 may be included within a separate unit (not shown) which may include a suitable power source (not shown).
  • a separate unit may be worn by the patient (such as, for example, by being attached to a belt worn by the patient, or carried in the patient's pocket, or the like).
  • the antenna 26 may be suitably coupled to the unit (not shown) by suitable insulated electrically conducting wires (not shown), or by other suitable electrical conductors. It is noted that to improve the signal to noise ratio in the measurement and to properly determine the resonance frequency of the sensor 10 (of Fig.
  • the antenna 26 and the sensor 10 may need to be suitably oriented and aligned relative to each other as is known in the art for loosely coupled transformers and passive resonant circuits.
  • the particular arrangement and alignment of the intraocular sensor (such as, for example, the sensor 10 of Fig. 3) and the external antenna (such as, for example, the antenna 26 of Fig. 3) relative to each other may depend, inter alia, on the structure, shape, and dimensions of the resonant circuit included in the sensor, and on the structure, shape, and dimensions of the external antenna, as is known in the art. Deviations from a substantially parallel arrangement of the electrical conductors
  • the spectacle-like frame or device may include an adjustable attaching mechanism (not shown) to adjust the alignment of the coil 26A relative to the resonant circuit 14 of the sensor 10.
  • the attaching mechanism may include adjustment screws (not shown) which may be turned to move the coil 26 relative to the spectacle-like frame or device (not shown).
  • Other, different, adjustment mechanisms or devices may be used for adjusting the position and/or orientation of the coil 26 relative to the spectacle-like frame or device, as is known in the art.
  • the advantage of such adjustment mechanisms is that they may allow the fine tuning and individual adjustment of the position and/or orientation of the coil 26 to each individual patient in accordance with the individual patient's sensor positioning within the eye, in order to compensate for individual differences in implantation position of the patient's sensor within the eye.
  • Another advantage is the ability of adjusting the position and/or orientation of the coil 26 to allow for individual differences in the facial and cranial anatomy of different patients, such as, but not limited to, the patient's inter-ocular distance, which may be necessary for optimization of the signal to noise ratio in an individual patient. It is noted that more than one sensor and more than one antenna may be used, for intraocular pressure measurement in more than one eye.
  • two implantable intraocular pressure sensors such as, but not limited to the sensor 10 of Fig. 3 may be implanted in the patient, one sensor may be implanted in each eye of the patient.
  • two antennas such as, for example, the antenna 26
  • the antennas may be integrated within or attached to spectacles or other types of frames which may be worn by the patient, as disclosed in detail hereinabove.
  • the structure and configuration of the sensor 10 illustrated in Figs. 1A, IB, and 3 is given by way of example only, and that many variations in the structure and configuration of the sensor may be made, including, but not limited to, modifications in the size, shape, configuration and composition of the annular housing of the intraocular sensor (such as, for example, the exemplary annular housing 12 of Figs. 1A and IB), and/or of any of the membranes included in the sensor's housing.
  • the structure and configuration of the sensor's resonant circuit may be made, including, but not limited to, modifications in the size, shape, configuration, and composition of the resonant circuit, and modifications in the distance between and the geometrical relationship between the components of the resonant circuit of the intraocular sensor (such as, for example, the exemplary spiral electrically conducting members 14A and 14B of the resonant circuit 14 of Figs. 1A and IB).
  • modifications in the size, shape, configuration, and composition of the resonant circuit such as, for example, the exemplary spiral electrically conducting members 14A and 14B of the resonant circuit 14 of Figs. 1A and IB.
  • Such design modifications in the sensor or it's components are considered within the scope and spirit of the present invention.
  • FIGS. 4A, 4B and 4C are schematic cross- sectional views illustrating various exemplary different types of intraocular implantable pressure sensors having different configurations, in accordance with additional embodiments of the present invention.
  • the sensor 40 may include an annular housing 12 similar to the annular housing 12 of the sensor 10 (of Fig. 1A).
  • the sensor 40 further includes a resonant circuit 44 attached to, or deposited on, or plated on the inner surface membranes 12A and 12B, as disclosed in detail hereinabove for the resonant circuit 14 of the sensor 10.
  • the resonant circuit 44 includes a first electrically conducting spiral member 44 A and a second electrically conducting spiral member 44B.
  • the first electrically conducting spiral member 44A may be attached to the first membrane 12 A
  • the second electrically conducting spiral member 44B may be attached to the second membrane 12B.
  • the spiral electrically conducting members 44A and 44B may be made from an electrically conducting material, such as, but not limited to, a metal, (such as, but not limited to, gold, silver, copper, or the like), or any other suitable electrically conducting material, as disclosed in detail hereinabove for the spiral members 14A and 14B of the sensor 10.
  • an electrically conducting material such as, but not limited to, a metal, (such as, but not limited to, gold, silver, copper, or the like), or any other suitable electrically conducting material, as disclosed in detail hereinabove for the spiral members 14A and 14B of the sensor 10.
  • Optically transparent, electrically conducting materials such as, but not limited to, indium-tin oxide (ITO) or the like, may also be used for forming the members 44A and 44B of the resonant circuit 44, or of any other resonant circuits of the present invention disclosed in detail hereinafter.
  • ITO indium-tin oxide
  • the spiral members 44A and 44B may be formed by forming a layer of a conducting material or metal on the internal surfaces 12E and 12F of the membranes 12A and 12B, respectively, followed by standard lithography methods, using various known techniques such as, photo-resist masking, etching, and the like, as is known in the art.
  • Other different methods for forming the spiral members 44A and 44B may also be used, such as, but not limited to, electroplating, chemical plating, sputtering, or the like, or any other suitable method known in the art.
  • spiral members 44 A and 44B are different than the spiral members 14A and 14B, in that while the spiral members 14A and 14B are not opposed to each other, but are rather interleaved, the spiral members 44A and 44B of the sensor 40 are opposed to each other (in a direction parallel to the axis 47 of the sensor 40) as illustrated in Fig. 4A.
  • the spiral electrically conducting member 44A may be electrically connected to the spiral electrically conducting member 44B by a suitable electrical conductor 44C.
  • the electrical conductor 44C may be any suitable electrically conducting member, such as, but not limited to, an electrically conducting wire, or flat ribbon, or the like.
  • the electrical conductor 44C may be suitably electrically connected to the spiral electrically conducting members 44A and 44B by any suitable method known in the art, such as, but not limited to, welding, gluing with an electrically conducting glue (not shown), wire bonding methods, or the like.
  • the electrical conductor 44C may be an electrically insulated conductor. However, the electrical conductor 44C may also be a non-insulated conductor. Similar to in the electrical conductor 14C, the electrical conductor 44C is configured such that it does not substantially hinder, prevent, or restrict the movement of the membranes 12A and 12B when the pressure outside the sensor 44 changes.
  • the electrical conductor 44C may be implemented in accordance with any of the layouts and implementations disclosed in detail hereinabove for the electrical conductor 14C (including, but not limited to, being attached to, or deposited on the internal or external surfaces, 12G and 12H of the membranes 12A and 12B, respectively, and being insulated or non-insulated).
  • the electrically conducting spiral members 44A and 44B may be electrically insulated by coating them or the surfaces 12E and 12F with a suitable thin layer of an electrically insulating material (the insulating material is not shown for the sake of clarity of illustration). However, the electrically conducting spiral members 44A and 44B may also be non-insulated conducting members.
  • the design of the resonant circuit 44 may be advantageous in that it may have a higher lumped capacitance value, due to the opposed relationship of the electrically conducting spiral members 44 A and 44B. As the membranes 12A and 12B move towards or away from each other, the lumped capacitance of the resonant circuit 44 may change, contributing to a change in the detectable resonance frequency of the resonant circuit 44.
  • the sensor 50 may include an annular housing 12 similar to the annular housing 12 of the sensor 10 (of Fig. 1A).
  • the sensor 50 may further include handling members 55A and 55B which may be attached, or glued, or otherwise suitably affixed to the housing 12.
  • the handling members 55 A and 55B may be used for handling and grasping the sensor 50 using any specially designed or standard surgical tool (not shown) during the surgical insertion procedures of inserting the sensor into an eye, as is known in the art.
  • the handling members 55A and 55B may be of any shape, dimensions, and material composition known in the art which is suitable for handling, grasping and/or folding of the sensor 50 (if the sensor 50 is implemented as a foldable sensor by suitable choice of materials and structural design).
  • the sensor 50 may further include a resonant circuit 54 attached to, or deposited on, or plated on the inner surfaces of the membranes 12A and 12B, as disclosed in detail hereinabove for the resonant circuit 14 of the sensor 10.
  • the resonant circuit 54 includes an electrically conducting spiral member 54A and a relatively broad electrically conducting loop member 54B formed as an annular layer having a gap therein forming an open loop.
  • the electrically conducting spiral member 54A may be attached to the first membrane 12 A, and the electrically conducting loop member 54B may be attached to the second membrane 12B.
  • the electrically conducting members 54A and 54B may be made from an electrically conducting material, such as, but not limited to, a metal, (such as, but not limited to, gold, silver, copper, or the like), or any other suitable electrically conducting material, as disclosed in detail hereinabove for the spiral members 14A and 14B of the sensor 10.
  • an electrically conducting material such as, but not limited to, a metal, (such as, but not limited to, gold, silver, copper, or the like), or any other suitable electrically conducting material, as disclosed in detail hereinabove for the spiral members 14A and 14B of the sensor 10.
  • Optically transparent, electrically conducting materials such as, but not limited to, indium-tin oxide (ITO) or the like, may also be used for forming the members 54A and 54B of the resonant circuit 54, or of any other resonant circuits of the present invention disclosed in detail hereinafter.
  • ITO indium-tin oxide
  • the members 54A and 54B may be formed by forming a layer of a conducting material or metal on the internal surfaces 12E and 12F of the membranes 12A and 12B, respectively, followed by standard lithography methods, using various known techniques such as, photo-resist masking, etching, and the like, as is l ⁇ iown in the art.
  • Other different methods for forming the members 54A and 54B may also be used, such as, but not limited to, electroplating, chemical plating, sputtering, or the like, or any other suitable method known in the art.
  • the members 54A and 54B are different than the spiral members 14A and 14B, in that the broad loop member 54B is a broad flat electrically conducting member opposed to the spiral windings of the spiral member 54 A (in a direction parallel to the axis 57 of the sensor 50) as illustrated in Fig. 4A.
  • Fig. 4C is a schematic top view of the membrane 12B of the sensor 50 of Fig. 4B.
  • the broad loop member 54B is attached to, or deposited on, or otherwise affixed to the inner surface 12F of the membrane 12B as illustrated.
  • the membrane 12B has a circular opening 51 therein.
  • the broad loop member 54B is shaped as an open loop having a gap 55 therein. It is, however noted that, in accordance with another embodiment of the present invention, the broad loop member 54B may also be configured as a closed loop (not shown in Fig. 4C) having no gap therein.
  • the handling member 55 A may be attached to or may form an integral part of the membrane 12B.
  • the handling member 55B (Fig. 4B) is not shown in Fig. 4C, and may be attached to or may form an integral part of the membrane 12 A as shown in Fig. 4B.
  • the handling members 55 A and 55B may both be attached to, or integral parts of the membrane 12B (this embodiment is not shown in Figs 4B and 4C).
  • the handling members 55 A and 55B may both be attached to, or integral parts of the membrane 12A (this embodiment is not shown in Figs 4B and 4C).
  • the spiral electrically conducting member 54 A may be electrically connected to the loop member 54B by a suitable electrical conductor 54C.
  • the electrical conductor 54C may be any suitable electrically conducting member, such as, but not limited to, an electrically conducting wire, or flat ribbon, or the like.
  • the electrical conductor 54C may be suitably electrically connected to the spiral electrically conducting member 54A and to the loop member 54B by any suitable method known in the art, such as, but not limited to, welding, gluing with an electrically conducting glue (not shown), wire bonding methods, or the like.
  • the electrical conductor 54C may be an electrically insulated conductor or may be a non-insulated conductor.
  • the electrical conductor 54C is configured such that it does not substantially hinder, prevent, or restrict the movement of the membranes 12A and 12B when the pressure outside the sensor 54 changes.
  • the electrical conductor 54C may be implemented in accordance with any of the layouts and implementations disclosed in detail hereinabove for the electrical conductors 14C and 44C (including, but not limited to, being attached to, or deposited on the internal or external surfaces, 12G and 12H of the membranes 12A and 12B, respectively, and being insulated or non-insulated).
  • the electrically conducting spiral member 54A and the loop member 54B may be electrically insulated by coating them, or the surfaces 12E and 12F, with a suitable thin layer of an electrically insulating material (the insulating material is not shown for the sake of clarity of illustration).
  • the electrically conducting spiral member 54A and the loop member 54B may, however, also be electrically non-insulated members.
  • the design of the resonant circuit 54 may be advantageous in that it may have a lumped capacitance value which may even be higher than the lumped capacitance value of the sensor 44 of Fig.
  • Fig. 5 is a schematic cross-sectional view illustrating another type of intraocular implantable pressure sensor having a resonant circuit including interdigitated electrical conducting members, in accordance with an additional embodiment of the present invention.
  • the sensor 60 may include an annular housing 62.
  • the housing 62 includes two membranes 62A and 62B which are sealingly attached to each other, by a suitable glue (not shown) or by thermal press welding, or by any other suitable method known in the art.
  • the annular housing 62 has a sealed space 66 therein.
  • the space 66 may be filled with a gas or a gas mixture as disclosed hereinabove for the space 16 of the sensor 10.
  • substantial parts of the inner surfaces 64E and 64F of the membranes 64 A and 64B, respectively, may be (optionally, but not obligatorily) substantially parallel to each other.
  • the membranes 62A and 62B of the sensor 60 may be different than the membranes 12A and 12B of the sensor 10 in shape and configuration
  • the membranes 62A and 62B may be made from flexible materials, such as, but not limited to, plastic materials, including, inter alia, PTFE, PP, PE and Parylene® C, or the like, as described in detail for the membranes 12A and 12B hereinabove.
  • the sensor 60 further includes a resonant circuit 64 attached to, or deposited on, or plated on the inner surfaces 64E and 64F of the membranes 62 A and 62B, respectively.
  • the resonant circuit 64 may include a first electrically conducting spiral member 64A and a second electrically conducting spiral member 64B.
  • the first electrically conducting spiral member 64A may be attached to the first membrane 62A
  • the second electrically conducting spiral member 64B may be attached to the second membrane 62B.
  • the spiral electrically conducting members 64A and 64B may be made from an electrically conducting material, such as, but not limited to, a metal, (such as, but not limited to, gold, silver, copper, or the like), or any other suitable electrically conducting material, as disclosed in detail hereinabove for the spiral members 14A and 14B of the sensor 10.
  • an electrically conducting material such as, but not limited to, a metal, (such as, but not limited to, gold, silver, copper, or the like), or any other suitable electrically conducting material, as disclosed in detail hereinabove for the spiral members 14A and 14B of the sensor 10.
  • Optically transparent, electrically conducting materials such as, but not limited to, indium-tin oxide (ITO) or the like, may also be used for forming the members 64A and 64B of the resonant circuit 64, or of any other resonant circuits of the present invention disclosed in detail hereinafter.
  • ITO indium-tin oxide
  • the spiral members 64A and 64B may be formed by forming a layer of a conducting material or metal on the internal surfaces 62E and 62F of the membranes 62 A and 62B, respectively, followed by standard lithography methods, using various known techniques such as, photo-resist masking, etching, and the like, as is known in the art.
  • Other different methods for forming the spiral members 64A and 64B may also be used, such as, but not limited to, electroplating, chemical plating, sputtering, chemical vapor deposition (CND) methods or the like, or any other suitable method known in the art for forming a layer of conducting material on a substrate.
  • the spiral members 64A and 64B are different than the spiral members 14A and 14B.
  • the thickness HI of the spiral member 64 A and the thickness H2 of the spiral member 64B may be substantially greater than the thickness of the spiral members 14A and 14B.
  • the thickness HI of the spiral member 64A may be equal to the thickness H2 of the spiral member 64B.
  • the thickness HI of the spiral member 64A may be larger or smaller than the thickness H2 of the spiral member 64B.
  • spiral members 64 A and 64B are also different than the spiral members 14A and 14B in that th'e spiral members 44 A and 44B are interdigitated, or interleaved such that the windings of the spiral member 64A may partially overlap some (or portions) of the windings of the spiral 64B along a direction parallel to the axis 67 of the sensor 60, as illustrated in Fig. 5.
  • the electrically conducting spiral member 64A may be electrically connected to the spiral electrically conducting member 64B by a suitable electrical conductor 64C.
  • the electrical conductor 64C may be any suitable electrically conducting member, such as, but not limited to, an electrically conducting wire, or flat ribbon, or the like.
  • the electrical conductor 64C may be suitably electrically connected to the spiral electrically conducting members 64A and 64B by any suitable method known in the art, such as, but not limited to, welding, gluing with an electrically conducting glue (not shown), wire bonding methods, or the like.
  • the electrical conductor 64C may be an electrically insulated conductor to prevent accidental short circuiting.
  • the insulation of the electrical conductor 64C may be implemented by using an electrical insulator layer 69 disposed over the electrical conductor 64C, or by using any other electrical insulation method known in the art.
  • the insulator layer 69 is a biocompatible insulator layer.
  • the electrical conductor for electrically connecting the spiral member 64A with the spiral member 64B may also be a non-insulated conductor (not shown) which may pass within the space 66 of the housing 62.
  • a design (not shown in Fig. 5) for the electrical conductor may be similar to the design illustrated for the electrical conductor 44C of the sensor 40 (of Fig. 4A).
  • the electrical conductor 64C may be sufficiently flexible, and may be configured such that it does not substantially binder, prevent, or restrict the movement of the membranes 62A and 62B when the pressure outside the sensor 64 changes.
  • the electrical conductor 64C may be implemented in accordance with any suitable configuration of the layouts and configurations disclosed in detail hereinabove for the electrical conductors 14C, 44C, and 54C (including, but not limited to, being attached to, or deposited on the internal or external surfaces, 62G and 62H of the membranes 62 A and 62B, respectively, and being insulated or non-insulated).
  • the electrical insulator layer 69 may be advantageous in preventing undesirable short circuiting, and in increasing the lumped capacitance of the resonant circuit 64 due to the high dielectric constant of the layer of electrically insulating material.
  • the design of the resonant circuit 64 of the sensor 60 may be advantageous in that it may have a higher lumped capacitance value, due to the partial overlap between the interdigitated electrically conducting spiral members 64A and 64B. As the membranes 62A and 62B move towards or away from each other, both the lumped capacitance of the resonant circuit 64, and the lumped inductance of the resonant circuit 64 may change substantially, and may thus contribute to a change in the detectable resonance frequency of the resonant circuit 44.
  • Fig. 6 is a schematic cross sectional view illustrating a composite implantable intraocular lens including a wireless intraocular pressure sensor, in accordance with another embodiment of the present invention.
  • the implantable composite lens 70 may include an optical lens body 72 and a wireless sensor 80 suitably attached to the lens body 72.
  • the sensor 80 may be similar in construction and operation to any of the sensors 10, 40, 50, and 60, disclosed hereinabove.
  • the sensor 80 may include a resonant circuit 84, which may be similar to the resonant circuit 14 of the sensor 10 in structure and operation.
  • the resonant circuit 84 may include a first spiral electrically conducting member 84A, a second spiral electrically conducting member 84B, and an electrical conductor 84C for electrically connecting the members 84A and 84C.
  • the first spiral electrically conducting member 84A, the second spiral electrically conducting member 84B, and the electrical conductor 84C may or may not be insulated, as disclosed in detail hereinabove for the first spiral electrically conducting member 14A, the second spiral electrically conducting member 14B and the conductor 14C of the sensor 10.
  • the lens body 72 may be any type of suitable implantable intraocular lens known in the art.
  • the details of the construction, design, and implantation of intraocular implantable lenses are well known in the art, are not the subject matter of the present invention and are therefore not disclosed in detail hereinafter.
  • the lens 72 may be attached to the sensor 80 by suitable attachment means.
  • the lens 72 may be attached to the sensor 80 by a suitable spacer member 74 (Fig. 6).
  • the lens 72 may be directly attached to the sensor 80 by a suitable biocompatible glue (not shown) or the like.
  • the lens 72, and the sensor 80 may be formed or manufactured as a single integrated unit.
  • the handling members 75 A and 75B may be suitably attached to the sensor 80.
  • the handling members 75A and 75B may be similar in design to the handling tabs or members used in intraocular implantable lenses, as is known in the art.
  • the handling members 75A and 75B may also be formed as an integral part of the sensor 80.
  • the handling members 75A and 75B may be used to handle the composite lens 70 during the lens implantation surgical procedure, as is l ⁇ iown in the art.
  • handling members 75A and 75B may have any suitable shape and configuration known in the art, and are not limited to the exemplary shape illustrated in Fig. 6.
  • the shape of the lens 72 illustrated in the exemplary embodiment of Fig. 6, is suitable for use for replacing the natural lens of a patient in cases were surgical procedures for extracting a cataract are performed, and in which the cataract is removed and the composite lens 70 may be inserted in its place.
  • the shape and dimensions of the lens 72 may be similar (but not necessarily identical to) to the shape and dimensions of implantable ocular lens (IOL) designs known in the art and usable for replacing the patient's natural lens (due to cataract formation or other reasons). It is, however, noted that in accordance with other embodiments of the composite lens of the present invention the lens 72 may be differently shaped to adapt the composite lens for other procedures.
  • the lens 72 may have other shapes and configurations which may be similar to implantable contact lens (ICL) designs, known in the art and suitable for implantation in front of (and not as a replacement of) the patient's natural lens in procedures which are l ⁇ iown in the art for correction of vision impairment of highly myopic patients.
  • ICL implantable contact lens
  • the ICL is surgically placed in front of the patient's natural lens without removing the natural lens.
  • the implantable composite lens (not shown) is placed adjacent to the lens 34 within the anterior chamber of the eye 30 similar to the placement of an ICL, the sensor included in the composite lens may enable the measurement of the pressure in the anterior chamber of the eye.
  • the components of the composite lens 70 may be flexible and foldable components, and may be made from suitably pliable and foldable materials in order to enable the folding of the composite lens 70 during it's insertion into the eye.
  • additional electrically conducting members may be included in the composite lens of the invention.
  • a thin spiral comprising an electrically conducting layer may be formed on or deposited upon or otherwise attached to the surface of the lens 72.
  • an optically transparent, electrically conducting spiral made from a thin layer of indium-tin oxide (ITO) may be attached on the surface 72A or on the surface 72B of the lens 72.
  • ITO indium-tin oxide
  • this spiral member may be disposed on the surface 72A or on the surface 72B near the peripheral part of the lens 72 close to the spacer member 74.
  • This electrically conducting spiral may be suitably electrically connected to one of the members 84A and 84B of the sensor 80 (which member may be in an open loop configuration) by a suitable electrically conducting connecting member (not shown).
  • the thin ITO layer of this electrically conducting spiral may be covered by a layer of transparent biocompatible material (layer is not shown), such as, but not limited to, Parylene® C, or the like, to prevent contact of the ITO with the vitreous body 32.
  • optically transparent, electrically conducting spiral disposed on the peripheral part of the lens 72 may be advantageous since it increases the number of windings in the resonant circuit (as compared to the number of windings of the members 84A and 84B of the sensor 80 taken alone) which may improve the tuning and performance of the resulting extended resonant circuit (not shown).
  • the use of an optically transparent material such as ITO in this additional spiral member may allow light to pass through the additional spiral member without undue impairment of visual function while significantly improving the performance and tunability of the resulting extended resonant circuit.
  • the various different embodiments of the composite lens of the present invention may be used for determining the intraocular pressure in combination with one or more external antenna and appropriate excitation/and detection circuitry (such as, but not limited to, the exemplary antenna 26 and the excitation and detection circuitry 35 of Fig. 3), or any other similar antenna and circuitry components usable for wireless intraocular pressure measurement known in the art.
  • one or more external antenna and appropriate excitation/and detection circuitry such as, but not limited to, the exemplary antenna 26 and the excitation and detection circuitry 35 of Fig. 3
  • any other similar antenna and circuitry components usable for wireless intraocular pressure measurement known in the art.
  • the parameters of the sensors and sensor components of the present invention may be modified or changed depending, inter alia, on the particular design and application of the sensor.
  • the parameters which may be modified by the person skilled in the art may include, but are not limited to, the shape, configuration, dimension and material composition of the sensor's housing (such as, but not limited to, the housing of the sensors 10, 40, 50, 60, and 80), the shape, dimensions, cross-sectional area, equivalent circuit electrical properties, and material composition of the resonant circuit included in the sensor (such as, but not limited to, the resonant circuits 14, 44, 54, 64, and 84), the shape, dimensions, cross-sectional area, material composition, and spatial interrelationship of the different components of the resonant circuit included in the sensor (such as, but not limited to, the electrically conducting members 14 A, 14B and the conductor 14C, the electrically conducting members 44A, and 44B, and the conductor 44C, the electrically conducting members 54A, 54B, and the conductor 54C,
  • housing of the sensors of the present invention may be modified into any suitable desired form of housing, including but not limited to, a flat annular housing, a flat regular polygonal annular housing, an annular housing having a flat ellipsoidal cross-section and a non-symmetrical housing having an irregular shape.
  • the passage or opening in the housing of the sensors of the present invention may be any suitable passage or opening suitable for passing light therethrough such as, but not limited to, a passage having a circular cross-section, a passage having a polygonal cross-section, a passage having an ellipsoidal cross-section, a passage having a regular polygonal cross-section, and any suitable type of irregularly shaped passage.
  • the sensors of the present invention may be implanted at various different positions within the vitreous body 32 of the eye 30.
  • the dimensions of the sensors (such as but not limited to the sensors 10, 40, 50, and 60), and the dimensions of the openings of the sensors (such as but not limited to the openings 20, 51, 61) may be adapted to, or designed in accordance with, inter alia, the desired distance between the lens of the eye and the implanted sensor (such as, for example, the desired distance between the lens 34 and the sensor 10 of Fig. 3).
  • the permissible distance between the lens such as, for example, the lens 34 of Fig.
  • the implanted sensor (such as, for example the sensor 10 of Fig. 3) and the implanted sensor (such as, for example the sensor 10 of Fig. 3) may be determined, inter alia, by the dimensions of the sensor's opening (such as, for example the opening 20 of the sensor 10), the dimensions, configuration, and electrical properties of the sensor's resonant circuit (such as, for example, the resonant circuit 14), and the dimensions, distance from the eye, configuration, and electrical properties of the excitation and detection circuitry coupled to the resonant circuit of the implanted sensor (such as, for example, the excitation and detection circuitry 35 of Fig. 3).
  • any other suitable desired optical element may be disposed within the passage or attached to the housing of the sensor.
  • the lens 72 of Fig. 6 may be substituted with another optical element, such as, but not limited to, an optical filter, a light polarizer, a multi-element lens, or the like.
  • more than one optical element may be attached to the sensor or disposed in the passage or opening of the sensor.
  • a multi-element lens may be attached or disposed or formed within the passage, or a combination of a lens (not shown) and an optical filter (not shown) may be attached or disposed or formed within the passage in any desired order, or alternatively, a single suitably dyed or colored lens may be disposed in the passage of the sensor 80 instead of the lens 72, and may serve as a lens and a filter.
  • Such pressure sensors including one or more optical elements may be implanted in the anterior chamber or in the posterior chamber of the eye as disclosed in detail hereinabove.
  • the conducting members included in the resonant circuits may be attached or disposed or glued or deposited on the internal surfaces of the membranes comprising the housing of the sensor or on the external surfaces of the membranes comprising the housing of the sensor (using suitable electrically insulating materials for any externally disposed conducting member), another possibility for configuring the sensor may also be used in some embodiments of the sensor.
  • the sensors 10, 40, and 50 may be modified by embedding the electrically conducting members of their respective resonant circuits within the membranes included in the housing of the sensors.
  • the conducting members 14A and 14B of the sensor 10 may be embedded within the membranes 12A and 12B , respectively, the conducting members 44A and 44B of the sensor 40 may be embedded within the membranes 12A and 12B of the sensor 40, respectively, and the conducting members 54A and 54B of the sensor 50 may be embedded within the membranes 12A and 12B, respectively of the sensor 50.
  • each membrane such as the membranes 12A and 12B
  • each membrane may be formed by preparing a first membrane (not shown) attaching or gluing or depositing a suitably shaped electrically conducting layer (not shown) on a surface of the first membrane and attaching or gluing or welding or depositing or otherwise forming a second membrane on top of the conducting layer, such that the electrically conducting layer is sandwiched between the first membrane and the second membrane, two such membranes each having an embedded conducting layer therein may then be joined or welded or glued or otherwise sealingly attached to each other to form the housing of a sensor in a way similar to that disclosed and illustrated for the membranes 12A and 12B of the sensors 10, 40 and 50 above.
  • the conducting members embedded within each of the two opposed joined membranes may be electrically coupled to form the resonant circuit by any method l ⁇ iown in the art, such as, for example, by removal of some insulating membrane material after the membranes are formed and electrically connecting the conducting member as disclosed hereinabove (using a conducting wire or ribbon or the like as disclosed in detail hereinabove), or by leaving suitably exposed portion of each of the electrically conducting members outside the membranes during the sandwiched membrane forming stage and electrically coupling the two electrically conducting members by suitable methods such as, but not limited to, welding, laser welding, soldering, connecting by electrically conducting glue, or by any other method known in the art for electrically connecting conducting materials or members.

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  • Measuring And Recording Apparatus For Diagnosis (AREA)

Abstract

L'invention a trait à un capteur de pression intraoculaire passif implantable. Le capteur comprend un logement fermé hermétiquement à l'intérieur duquel est ménagé un passage. Ledit passage permet à la lumière de circuler et d'atteindre la rétine. Le logement du capteur possède des parois formant une chambre fermée hermétiquement. Au moins l'une des parois du logement se présente sous la forme d'une paroi mobile, configurée pour se déplacer ou se déformer en réponse à des modifications de la pression présente à l'extérieur du capteur. Le capteur comprend un circuit résonant électromagnétique passif. Au moins une partie dudit circuit est couplée par voie mécanique à une ou plusieurs des parois mobiles ou déformables du logement, de façon que la fréquence de résonance du circuit résonant varie en fonction de la pression présente à l'extérieur du capteur. Le passage ménagé à l'intérieur du logement peut être ouvert ou, dans une autre variante, un ou plusieurs éléments optiques tels qu'une lentille intraoculaire, des filtres ou autres peuvent être placés dans le passage pour modifier la lumière circulant à travers ce dernier. L'invention concerne également un système utilisé avec les capteurs intraoculaires implantables et des procédés d'implantation des capteurs.
PCT/IL2003/000163 2002-03-05 2003-03-03 Capteur intraoculaire WO2003073959A2 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU2003214592A AU2003214592A1 (en) 2002-03-05 2003-03-03 Implantable passive intraocular pressure sensor

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US36136102P 2002-03-05 2002-03-05
US60/361,361 2002-03-05

Publications (2)

Publication Number Publication Date
WO2003073959A2 true WO2003073959A2 (fr) 2003-09-12
WO2003073959A3 WO2003073959A3 (fr) 2003-12-04

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AU (1) AU2003214592A1 (fr)
WO (1) WO2003073959A2 (fr)

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2423368A (en) * 2005-02-22 2006-08-23 Depuy Int Ltd Push-fit body implantable position sensor
GR20060100324A (el) * 2006-06-01 2008-02-05 Πασχαλης Ελευθεριος Νεο ευκαμπτο ενδοφθαλμιο τονομετρο (ετ) καταγραφης της ενδοφθαλμιας πιεσης επι ενδοφακου
WO2010061207A1 (fr) * 2008-11-01 2010-06-03 University Of Dundee Dispositif de mesure de pression
WO2010100654A2 (fr) * 2009-01-30 2010-09-10 Panduranga Revankar Krishna Prasad Dispositif permettant à une personne de surveiller directement sa pression intraoculaire en fonction des variations de motifs et de couleurs
EP2347702A1 (fr) * 2010-01-22 2011-07-27 Ophtimalia Système multidiagnostic sans contact utilisant des paramètres physiologiques oculaires
CN105120736A (zh) * 2013-04-19 2015-12-02 弗托诺公司 利用电磁波的测量方法和布置
US9307905B2 (en) 2012-09-14 2016-04-12 University Of Washington Intraocular pressure sensing devices and associated systems and methods
US9848775B2 (en) 2013-05-22 2017-12-26 The Board Of Trustees Of The Leland Stanford Junior University Passive and wireless pressure sensor
CN115517635A (zh) * 2022-09-26 2022-12-27 天津大学 一种无源植入式血液状态监测传感器件及其制备方法

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US4385636A (en) * 1978-05-23 1983-05-31 Cosman Eric R Telemetric differential pressure sensor with the improvement of a conductive shorted loop tuning element and a resonant circuit
US5005577A (en) * 1988-08-23 1991-04-09 Frenkel Ronald E P Intraocular lens pressure monitoring device
US6193656B1 (en) * 1999-02-08 2001-02-27 Robert E. Jeffries Intraocular pressure monitoring/measuring apparatus and method

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4385636A (en) * 1978-05-23 1983-05-31 Cosman Eric R Telemetric differential pressure sensor with the improvement of a conductive shorted loop tuning element and a resonant circuit
US5005577A (en) * 1988-08-23 1991-04-09 Frenkel Ronald E P Intraocular lens pressure monitoring device
US6193656B1 (en) * 1999-02-08 2001-02-27 Robert E. Jeffries Intraocular pressure monitoring/measuring apparatus and method

Cited By (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7756579B2 (en) 2005-02-22 2010-07-13 Depuy International Ltd. Implantable sensor
GB2423368A (en) * 2005-02-22 2006-08-23 Depuy Int Ltd Push-fit body implantable position sensor
GR20060100324A (el) * 2006-06-01 2008-02-05 Πασχαλης Ελευθεριος Νεο ευκαμπτο ενδοφθαλμιο τονομετρο (ετ) καταγραφης της ενδοφθαλμιας πιεσης επι ενδοφακου
GB2476762A (en) * 2008-11-01 2011-07-06 Univ Dundee Pressure measurement device
WO2010061207A1 (fr) * 2008-11-01 2010-06-03 University Of Dundee Dispositif de mesure de pression
GB2476762B (en) * 2008-11-01 2012-01-18 Univ Dundee Pressure measurement device
WO2010100654A2 (fr) * 2009-01-30 2010-09-10 Panduranga Revankar Krishna Prasad Dispositif permettant à une personne de surveiller directement sa pression intraoculaire en fonction des variations de motifs et de couleurs
WO2010100654A3 (fr) * 2009-01-30 2010-11-04 Panduranga Revankar Krishna Prasad Dispositif permettant à une personne de surveiller directement sa pression intraoculaire en fonction des variations de motifs et de couleurs
US9282891B2 (en) 2009-01-30 2016-03-15 Sundaraja Sitaram Iyengar Monitoring intra ocular pressure using pattern and color changes
EP2347702A1 (fr) * 2010-01-22 2011-07-27 Ophtimalia Système multidiagnostic sans contact utilisant des paramètres physiologiques oculaires
US9307905B2 (en) 2012-09-14 2016-04-12 University Of Washington Intraocular pressure sensing devices and associated systems and methods
CN105120736A (zh) * 2013-04-19 2015-12-02 弗托诺公司 利用电磁波的测量方法和布置
US9848775B2 (en) 2013-05-22 2017-12-26 The Board Of Trustees Of The Leland Stanford Junior University Passive and wireless pressure sensor
CN115517635A (zh) * 2022-09-26 2022-12-27 天津大学 一种无源植入式血液状态监测传感器件及其制备方法

Also Published As

Publication number Publication date
AU2003214592A8 (en) 2003-09-16
AU2003214592A1 (en) 2003-09-16
WO2003073959A3 (fr) 2003-12-04

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