WO2015138507A1 - Système optique sans fil de correction de la presbytie - Google Patents

Système optique sans fil de correction de la presbytie Download PDF

Info

Publication number
WO2015138507A1
WO2015138507A1 PCT/US2015/019781 US2015019781W WO2015138507A1 WO 2015138507 A1 WO2015138507 A1 WO 2015138507A1 US 2015019781 W US2015019781 W US 2015019781W WO 2015138507 A1 WO2015138507 A1 WO 2015138507A1
Authority
WO
WIPO (PCT)
Prior art keywords
sensor
chamber
assembly
lai
fibers
Prior art date
Application number
PCT/US2015/019781
Other languages
English (en)
Inventor
Valdemar Portney
Original Assignee
Valdemar Portney
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
Priority claimed from US14/642,236 external-priority patent/US9931203B2/en
Application filed by Valdemar Portney filed Critical Valdemar Portney
Priority to EP15762170.7A priority Critical patent/EP3116443A4/fr
Publication of WO2015138507A1 publication Critical patent/WO2015138507A1/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A61B5/0031—Implanted circuitry
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/1107—Measuring contraction of parts of the body, e.g. organ, muscle
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16—Intraocular lenses
    • A61F2/1613—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • A61F2/1624—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside
    • A61F2/1635—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside for changing shape
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0247—Pressure sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0001—Means for transferring electromagnetic energy to implants
    • A61F2250/0002—Means for transferring electromagnetic energy to implants for data transfer
    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C7/00—Optical parts
    • G02C7/02—Lenses; Lens systems ; Methods of designing lenses
    • G02C7/08—Auxiliary lenses; Arrangements for varying focal length
    • G02C7/081—Ophthalmic lenses with variable focal length

Definitions

  • the present invention relates generally to a sensor interacting with ciliary muscles that transmits a signal to an ophthalmic lens to change its optical power between far and near foci. More particularly, the present invention relates to the sensor cell that responds to pressure or electric field change with ciliary muscles contraction or and relaxation with accommodation and disaccommodation, and to transmit data corresponding to accommodation or disaccommodation to activate an ophthalmic adjustable lens for switching between far and near foci. The present invention also relates to the system of wireless communication between a sensor cell that responds to pressure or electric field change by ciliary muscles contraction and relaxation with accommodation and disaccommodation for communication with dual- chamber adjustable ophthalmic lens activated by electrostatic force for switching between far and near foci.
  • the ciliary body has three basic functions, (a) aqueous production and removal through the trabecular meshwork to collect it in Schlemm's canal, (b) accommodation, and (c) formation of vitreous mucopolysaccharide (it acts like binding, lubricating element).
  • Accommodation function is the central subject of the present invention and ciliary muscles confined by the ciliary body play central role in this function.
  • the ciliary muscles consist of longitudinal, radial, and circular muscles fibers.
  • the greater part of ciliary muscles is composed of longitudinal fibers running anterior-posterior (front-to-back) on the inner aspect of the sclera (outer layer of the eye called white of the eye) about 8 mm behind the limbus (border of the cornea as transparent part of the eye and sclera.
  • the longitudinal fibers are attached by tendinous insertions to the elastic choroid.
  • the longitudinal fibers are attached to the scleral spur.
  • Accommodation is the ability of eye to focus on far and near objects without an optical aid. Near vision occurs with ciliary muscle contraction that changes ciliary body shape with the help of elastic choroid and scleral spur both acting as muscle anchors in the eye. Far vision (disaccommodation) occurs with ciliary muscle relaxation also with the help of elastic choroid and scleral spur.
  • the area in and at the ciliary muscles around a scleral spur is: (a) active area during accommodation / disaccommodation in terms of ciliary muscles actions and (b) accessible for a surgical procedure as being likely a minor modification of already well developed glaucoma surgical procedure such as glaucoma shunt installed close to trabecular meshwork.
  • Presbiopia condition is generally defined as the inability to see at far and near distances without an optical aid where far is commonly defined as a distance of 4 meters and beyond from the eye and near is a distance of 50 cm and closer to the eye with a distance in between is referenced to as intermediate distance.
  • the presbyopia develops due to inability of a natural crystalline lens to change its shape for its optical power change between far and near foci.
  • NFC radio-frequency Communication
  • RFID radio frequency identification
  • NFC uses magnetic induction between two loop antennas (transponder and target) located within each other's near field (reading distance), effectively forming a transformer.
  • NFC operates within the globally available and unlicensed radio frequency ISM band (as opposed to where additional security is required over traditional RFID tag) due to a very short reading distance, typically 10 cm or shorter but may be up to about 20 cm with a weaker interaction. The corresponding reading distance is adequate for communication by only one implanted sensor cell with adjustable lenses at both eyes in bilateral placement and, at the same time, to minimize interference from other external devices.
  • Near field RFID uses magnetic induction between a reader and a transponder. If an RFID tag (transponder) is placed within range of the reader, the alternating voltage appears across it and the magnetic field is affected by data stored on the tag. The voltage is rectified and powers the tag. As it is powered, the data are sent to the reader.
  • RFID tag transponder
  • NFC Interaction is based on a message/reply system. A device that begins the interaction process is called the “initiator” and the other called the "target”. NFC-enabled device A as initiator sends a message to a NFC-enabled device B as a target, device B then responds as the device B cannot send data without being contacted first by the initiator (device A).
  • NFC forgoes the "pairing" process between NFC-enabled devices entirely contrary to other M2M technologies (Bluetooth, Wi-Fi) though other wireless technology can also be applied in the present invention.
  • NFC-enabled device allows automatic "pairing” and effortless communication and control of data transfer.
  • micro batteries In terms of a power source to power the sensor cell and adjustable lens there are two types of power supply: micro batteries or radio-power transmission by inductance.
  • Thin-film micro batteries are composed of successive sub-micron to several micron-thick layers of cathode (UC0O2 or LiMn20 ), lithium phosphorus oxynitride (LIPON) electrolyte and a lithium or silicon tin oxynitride anode.
  • Planar batteries have cathodes with thicknesses of up to 5 micron and might be applicable for a sensor cell in rechargeable form by inductance.
  • An adjustable optic might be powered by photocell because accommodation is not required at low light condition, specialized micro battery or by inductance from the sensor cell. In short, multiple power solutions are possible.
  • the ciliary sulcus ring sensor such as an electromyographic receiver which detects a signal created by the ciliary muscle.
  • the sensor includes miniaturized electrodes for implanting into the ciliary muscle of the subject and a microcomputer modulates the ciliary muscle signal detected by the sensor(s) into an electrical signal for transmittance to a micromotor, which causes compression of the IOL via an annular support ring system to change lens power.
  • a placement the sensors at the ciliary ring creatures an uncertainty with the ciliary muscle electrodes position and quality of signal. There is uncertainty with a depth of the electrodes and also an eye sulcus diameter varies. This is additional uncertainty between the individual differences with signal characteristics which has not been addressed.
  • Another complexity is the use of micromotor to compress the lens for optical power change.
  • U.S. Patent 8,778,022 by Blum shows a stabilized electro active lens which can be remotely programmed.
  • This patented lens includes an electro active element and a view detector. The electro-active element provides vision
  • the element may include polymer gels, liquid crystals, pixilated grid elements, transparent electrodes and insulators, and similar devices
  • the U.S. Patent 8,857,983 by Pugh describes an ophthalmic lens consisting of a die structure of layers with mounted on one of them electronic components that includes antenna for electro-magnetic communication and inductive coupling for energy charging.
  • the electronic arrangement is described for a general lens use such as data to be transmitted or received may include tear film analysis, intra ocular pressure, heart rate, blood pressure, to sense ciliary muscle contraction for an accommodating lens and like without disclosing a specific sensor mechanism for providing such data.
  • the publication described a number of difficulties for continuous communication without providing descriptions how to reduce the described concepts to practice.
  • the publication hasn't described a specificity of a sensor positioning and supporting it in or on the eye and being more on a conceptual level. This is additional uncertainty between the individual differences with signal characteristics which has not been addressed and a definition of calibration.
  • the ciliary muscles mechanics is a complex system and it would be desirable to achieve a continuous focus from far to near but such a system presents the immense difficulty which has not been addressed by the application.
  • a sensor cell may be implanted at any part of the ciliary muscle for its mechanical (pressure) or/and electromyographic (EMG) interaction with them via mechanical (pressure) probe(s) or electrical field by EMG electrod(s) but it is more practical to apply it to the area around the scleral spur.
  • a sensor cell incorporates electronic processing to transfer a signal from the pressure probe or EMG electrode into usable electric signal which involved digitization, amplification and processing.
  • a sensor cell also incorporates a microchip for wireless
  • a wireless communication is used such as Near Field Communication (NFC) or Super Bluetooth or any other wireless technology though it is preferably to utilize a short range communication such as NFC due to its advantages.
  • NFC Near Field Communication
  • Super Bluetooth any other wireless technology though it is preferably to utilize a short range communication such as NFC due to its advantages.
  • the senor it might be desirable for the sensor to include several pressure probes at different parts of the sensor that can be located at the opposite sides of the muscles at the scleral spur area in order to improve a quality of signal. It may also be advantageous to include the interaction with different muscle fibers to improve the quality of signal.
  • the signal is electronically transformed into a more meaningful form such as a digital signal representation, which can be amplified it to enable analysis.
  • Placement of pressure sensor with its pressure probe(s) and EMG sensor with its electrode(s) is important. For instance, it is desirable in case of EMG sensor for instance, to place several electrodes along the imaginary line that joins them to be parallel to the muscular fiber orientation, i.e. front-to-back of the eye if interacting with longitudinal fibers or perpendicular to front-to-back line if considering radial fiber.
  • the central part disclosed by the present invention involves signal identification.
  • the signal generated by the sensor during stimulation by the ciliary muscles contraction and relaxation is recorded.
  • the actual visualization of ciliary body contour change during ciliary muscles contraction and relaxation is also recorded by, for instance, by high frequency ultrasound biomicroscopy (UBM) to insure that stimulation actually results in ciliary muscles contraction and relaxation to avoid faults signals.
  • UBM ultrasound biomicroscopy
  • the sensor cell signal is digitized, processed and filtered and the next step is to convert the signal into identification signals associated with ciliary muscles states, i.e. contraction and relaxation, though it is also possible to have ciliary muscles states identification for 3 states - contraction, relaxation and in-between.
  • the process involves time synchronization between the sensor cell signal and ciliary body visualization signal.
  • the visualization signal is divided into ranges associated with the relaxation state and contraction state and the convenor transforms the timed synchronized ranges of sensor cell signal associated with the selected visualization range of relaxed muscles into the convenor data for relaxation state, say signal "1 ", and the sensor cell signal associated with the selected range of contracted muscles into the convenor signal for contraction state, say signal "0".
  • the process is called the sensor cell ciliary muscle identification for ciliary muscle states and
  • the adjustable lens receives the signal “1 ", it changes its optical condition to far focus and if it receives the signal "0", it changes its optical condition to near focus. In case of identification of 3 states, i.e. also in-between identification for intermediate by the corresponding signal "2", the adjustable lens takes the optical condition for intermediate focus. This is so called communication by the identification data.
  • the receiver via the processor changes the optical state of the adjustable optic accordingly.
  • they need some sort of calibration to establish a correlation between the action (sensor cell interaction with muscles) and reaction (adjustable optic power state change).
  • the "calibration" is very uncertain and likely difficult.
  • the embodiments disclosed herein avoids such complexity by introducing identification data, which is a digitized correlation between action (sensor cell interaction with muscles) and reaction (adjustable optic power state change).
  • the establishing identification data involves analyzing the actions of the ciliary muscles in terms of establishing that a certain range of the muscle's change is defined as “muscles contraction” and another range of ciliary muscle's change is defined as “muscles relaxation”.
  • the processor of the sensor cell is programmed to transmit identification data instead of a sensor sell signal. It means if a sensor cell signal is within the range corresponding to the "muscles contraction", the sensor cell transmitter transmits the identification data, say, "1 " and if within the range of "muscles relaxation” the transmitted identification data is "0".
  • an adjustable optic any type, not just dual-chamber fluidic lens
  • receives identification data "1” it changes to a higher optical power
  • identification data "0” is received it changes to a lower optical power.
  • the present invention has also addressed a question of securing communication between a given sensor cell with corresponding adjustable optic. This is to avoid an inadvertent communication of the adjustable optic with a different censor cell or even other wireless devices.
  • the sensor cell ID is used to establish unique recognition of the signal between the sensor cell and adjustable optic.
  • the present invention has also addressed a question of bilateral placement of adjustable lenses for right and left eyes and ciliary muscle action during accommodation. Accommodation is commonly equivalent between the eyes and only one sensor cell implantation is required to control bilateral placement of adjustable optic lenses with the introduction of identification data. Similar as above, sensor ID is used to establish unique communication with both adjustable optics by programming the ID into their RFID tags.
  • the present invention also discloses dual-chamber electrostatically activating fluidic lens as a desirable option for a wireless system that includes a sensor cell that responds to ciliary muscles contraction and relaxation for the signal transmission to the adjustable lens.
  • a sensor cell that responds to ciliary muscles contraction and relaxation for the signal transmission to the adjustable lens.
  • This type of adjustable lens acts as opto-mechanical transistor where the optical powers for far and near foci are set by the lens design itself.
  • the corresponding optic is called RDS optic and it allows a reduction of necessary processing power because it is inherently digital by design due to switching between preset far and near foci if a signal is below set threshold or above it. It also reduced power consumption as the power is used only to change to preexisting optical power state of the RDS optic without a need to continually control the optical power state of the lens.
  • FIG. 1 illustrates a portion of eye anatomy responsible for the
  • FIG. 2 illustrates a portion of eye anatomy responsible for the
  • FIG. 3 illustrates a portion of eye anatomy responsible for the
  • FIG. 4 illustrates a portion of eye anatomy responsible for the
  • FIG. 5 illustrates a portion of eye anatomy responsible for the
  • FIG. 6 demonstrates a side view of a dual-element pressure sensor cell for differential signal detection of ciliary muscles actions
  • FIG. 7 demonstrates a front view of a dual-element pressure sensor cell for differential signal detection of ciliary muscles contraction and relaxation;
  • FIG. 8 demonstrates a side view of a one-element EMG sensor cell for electrical field measurements caused by ciliary muscles contraction
  • FIG. 9 shows a diagram of a sensor cell process of measuring ciliary muscle contraction and relaxation, ciliary muscle actions visualization and
  • FIG. 10 demonstrates cross-section of dual-chamber fluidic lens activated by electrostatic force directly at the holding chamber. The lens being in relaxed state for far focus when the force is not applied;
  • FIG. 1 1 demonstrates cross-section of two-chamber fluidic lens of Fig. 9 activated by electrostatic force directly at the holding chamber and being in active state for near focus when the force is applied;
  • FIG. 12 demonstrates cross-section of dual-chamber fluidic lens activated by electrostatic force indirectly at the holding chamber by applying it to the control chamber and being in relaxed state for near focus when the force is not applied;
  • FIG. 13 demonstrates cross-section of dual-chamber fluidic lens of Fig. 1 2 activated by electrostatic force indirectly at the holding chamber by applying it to the control chamber and being in active state for far focus when the force is applied;
  • FIG. 14 demonstrates cross-section of RDS optic design activated by electrostatic force indirectly on the holding chamber by applying it to the control chamber and being in relaxed state for far focus when the force is not applied; and
  • FIG. 15 demonstrates cross-section of RDS optic design of Fig. 14 activated by electrostatic force indirectly on the holding chamber by applying it to the control chamber and being in active state for near focus when the force is applied.
  • FIG. 1 illustrates a portion 1 00 of eye anatomy responsible for the accommodation process shown as the eye's cross section.
  • the Figure 1 includes implanted aphakic intra-ocular lens 180 that replaces natural lens.
  • the ciliary muscles accommodating apparatus is confined by ciliary body 140 and is divided into longitudinal fibers 1 1 0, radial fibers 120 and circular fibers 130 each having different orientation and, as a result, contracting in different planes.
  • the longitudinal fibers 1 1 0 attach to the scleral spur 150
  • the radial 1 20 and circular fibers 130 attach to the back of the trabecular meshwork 160 and posterior wall of the iris 1 70.
  • Radial fibers 120 are composed of few thin fibers that contracts during disaccommodation (from near to far focus) to focus far objects by pulling out the equatorial part of the eye's capsular bag of the natural lens. Most of circular fibers 130 run in a circle around the ciliary body 140 concentrically with the root of iris 170. During accommodation, (from far to near focus) their sphincter like action constricts the ciliary ring around the natural lens to act synergistically with longitudinal fibers 1 1 0 to pull the ciliary body 140 forward and inward by up to about 0.5 mm to focus near objects. The change of a ciliary body during accommodation and disaccommodation can be observed by high frequency ultrasound
  • UBM biomicroscopy
  • sensor cell signal particularly EMG signal
  • UBM independent visualization of the ciliary body movement with accommodation and disaccommodation
  • FIG. 2 illustrates a portion 200 of eye anatomy responsible for the accommodation process with implanted corneal implant (corneal inlay) 280 at the cornea 270 and sensor cell 290 at the exterior of longitudinal fibers 210 at the vicinity of scleral spur 250.
  • the Figure 2 also includes natural lens 240 surrounded by the capsular bag.
  • the ciliary muscles accommodating apparatus is divided into longitudinal fibers 21 0, radial fibers 220 and circular fibers 230 each having different orientation and, as a result, contracting in different planes.
  • FIG. 3 illustrates a portion 300 of eye anatomy responsible for the accommodation process shown as the eye's cross section.
  • the Figure 3 includes implanted aphakic intra-ocular lens 380 that replaces natural lens.
  • the ciliary muscles accommodating apparatus is divided into longitudinal fibers 310, radial fibers 320 and circular fibers 330.
  • Sensor cell 350 is placed at the vicinity of scleral spur 370 at close proximity to circular fibers 330 to respond to their contraction with accommodation and relaxation with disaccommodation.
  • FIG. 4 illustrates a portion 400 of eye anatomy responsible for the accommodation process shown as the eye's cross section.
  • the Figure 4 includes implanted aphakic intra-ocular lens 460 that replaces natural lens.
  • the ciliary muscles accommodating apparatus is divided into longitudinal fibers 410, radial fibers 420 and circular fibers 430.
  • Dual-element sensor cell consists of element 450 that is placed at the vicinity of scleral spur 440 at close proximity to the longitudinal fibers 410 and element 455 also placed at the vicinity of scleral spur 440 at close proximity to the circular fibers 430 to respond to their contraction with
  • Dual-element sensor cell is useful with its higher response quality which is particularly beneficial for EMG sensor cell.
  • FIG. 5 illustrates a portion 470 of eye anatomy responsible for the accommodation process shown as the eye's cross section.
  • the ciliary muscles accommodating apparatus is confined by ciliary body 480 and includes longitudinal fibers 485.
  • One element 500 of the dual-element sensor cell is placed at the vicinity of scleral spur 490 at close proximity to longitudinal fibers 485 and another element 505 is placed at the opposite side of the scleral spur 490.
  • the elements can be connected by a flexible member.
  • This dual-element sensor cell is particularly beneficial for pressure sensor cell for differential pressure measurements with ciliary muscles contraction with accommodation when the anterior tendon incorporating the scleral spur 490 is pulled in toward the ciliary muscles thus increasing a pressure on the element 500 and reducing pressure at the element 505. The pulling force drops with disaccommodation thus reducing pressure differential.
  • the dual-element sensor cell might have a different arrangement with one element placed against the circular fibers and another opposite side of the scleral spur.
  • FIG. 6 demonstrates a dual-element pressure sensor cell 510 per this example consisting of two elements 520 and 525 with elastic elements 530 and 540 at each sensor cell element.
  • the elements 520 and 525 of the sensor cell 510 are connected by flexible member 545 and both placed externally and internally to the ciliary muscle fibers with the scleral spur situated closely in between to create a differential pressure between the elastic elements 530 and 540 of the sensor cell 510 with ciliary muscle contraction and relaxation.
  • Each plate 520 and 525 has hard exterior shell 550 or 560 correspondently and pressure detecting elements 570 or 580 to respond to the force exerted by the ciliary muscle.
  • Mechanical pressure sensor may be similar to an electrostatic (capacitor type) design - mechanical force changes separation between electric plates thus changing an electrical signal of the electronic circuitry though the conversion of the mechanical force into electrical signal or can be based on other designs. For instance, by sandwiching ultrathin gold nanowire between two thin polydimethylsiloxane sheets and flexing the sheets changes the current through the wire.
  • the advantage of such design is that the sensor can resolve pressing, bending, torsional forces and even vibrations to filter the useful signal more precisely.
  • the pressure differentiation signal is digitized, amplified and electronically processed. It then is converted into ciliary muscle identification data (CMID) corresponding to certain ranges of pressure defined as accommodation and disaccommodation.
  • CMID ciliary muscle identification data
  • the CMID is transmitted to the adjustable optic to increase optical power with accommodation or reduce optical power with disaccommodation.
  • the elastic element changes its shape due to pressure change which is converted into electrical signal by different principles: electrostatically or variable capacitance, conductivity change due to bending a conducting wire, etc..
  • FIG. 7 illustrates sensor cell 51 0 exterior view facing outside the eye, i.e. front view of the element 525 with the elastic element 530 inside.
  • the electronic part 590 serves for processing and signal transmission and its position within the sensor cell varies.
  • the sensor cell can be of different shape and construction. Dimensionally, there is a benefit to be within dimensions of a glaucoma shunt as the placement of the sensor cell is anatomically close to the common placement of a glaucoma shunt at the trabecular meshwork.
  • the dimensions are about 10 mm width / length and about 2 mm thick which can relate to any type of sensor cell.
  • the dimensions are adequate for planar batteries that have cathodes with thicknesses of up to 5 micron and multiple batteries be placed behind hard exteriors of the sensor cell elements.
  • FIG. 8 demonstrates an example of single element EMG sensor cell 600.
  • EMG is a technique in which the electric field characteristic surrounding the muscle is measured.
  • Implantable myoelectric sensors have been developed for surface and intramuscular electromyogram recording. The later is used in the EMG sensor cell. Because the detected electric field is relatively small (in the range of 10 - 4 -10 "3 V), amplification is used to enhance the electrical signal.
  • Electromyography sensor collects electric samples at high rate, like 1000 Hz in multiple channels.
  • EMG amplifier is used as a differential amplifier that subtract the value between the electrodes. Electrodes placement is important in relation to muscular fibers, they are placed along the fibers.
  • the electrodes in one element are along longitudinal fibers and electrodes in other element are along circular fibers.
  • FIG. 9 illustrates a block diagram of setting up and conducting wireless communication between a sensor cell and adjustable optic.
  • accommodation for near focus corresponds to contraction of longitudinal and circular fibers of ciliary muscles and disaccommodation to relaxation of the corresponding fibers.
  • the fibers effect on the sensor cell via pressure probes or EMG electrodes is shown by lines 1 .
  • pressure probes or EMG electrodes, block 620 generate electrical signal from the ciliary fibers actions which electronically processed as explained above, block 640.
  • Visual information of the ciliary body contour change during ciliary muscles contraction and relaxation is also collected by UBM (ultrasound biomicroscopy), lines 2.
  • the UBM measures the change in the ciliary body contours as it is known that the ciliary body center of gravity moves forward and inward with fibers contraction during accommodation.
  • the visualization is defined by a change of the center of gravity of the ciliary body contour or by any other parameter associated with the ciliary body contour change.
  • the corresponding electronic signal is called visualization signal. This objective measurement of ciliary fibers action is required because it is the only verifiable way to test for accommodation / disaccommodation in a presbyopic subject.
  • the visualization device collects the images of ciliary body contours, block 630, processes them into useful electronic visualization signal, block 650.
  • Sensor cell convenor, block 660 collects visualization signal from visualization processor, block 650, as shown by line 3, and together the visualization signal and signal from the sensor cell are time superimposed to general ciliary muscle identification data (CMID).
  • CMID general ciliary muscle identification data
  • the ranges of visualization signal corresponding to accommodation and disaccommodation are established independently by the scientific analysis.
  • the sensor cell convenor 660 establishes the range of sensor cell signal corresponding to the established visualization signals for accommodation and disaccommodation to generate corresponding ciliary muscle identification data (CMID) that act as the switching signals for an adjustable optic, say "1 " signal for disaccommodation and "0" signal for accommodation.
  • the adjustable optic switches to higher optical power for near focus, if the signal "1 ", it switches to lower optical power for far focus.
  • the CMID is transmitted to an adjustable optic for its optical power control as shown by lines 7 and 7' which is also beneficial with commonly used bilateral application of two adjustable optic lenses for left and right eyes. This takes into consideration that ciliary muscles activities for accommodation and disaccommodation are usually equivalent in both eyes and only one sensor cell implantation is required.
  • the NFC-enabled sensor cell initiator / reader in the reading mode initiates NFC-enabled adjustable optic target / transponder
  • the adjustable optic transponder provides data on sensor cell ID for the censor cell reader to recognize the adjustable optic by the sensor cell with the same ID.
  • the sensor cell than uses P2P mode to pass CMID signal to the adjustable lens to increase its optical power for near focus or reduce its optical power for far focus.
  • An accommodation reflex time is a fraction of second and wireless communication does not present an issue with accommodation respond time.
  • Adjustable lens may be a phakic intraocular lens, aphakic intraocular lens, corneal implant (inlay), contact lens or spectacle lens.
  • aphakic intraocular lens may be aphakic intraocular lens, aphakic intraocular lens, corneal implant (inlay), contact lens or spectacle lens.
  • Single sensor cell of the present invention that includes identification data is set to communicate with any number of adjustable lenses.
  • FIG. 10 demonstrates dual-chamber fluidic adjustable optic of intraocular lens 700 shaped for a typical aphakic implantation. It includes transparent chamber 710 that effects the optical power of the lens 700 due a change in its shape by the elastic membrane 720 and another, so called holding chamber 740 which shape is controlled by electrostatic force. Both are filled with an optical fluid.
  • the transparent chamber covers the optical aperture of the lens, about 4-6 mm diameter, i.e. it is image forming part of the lens 700.
  • the other side of the transparent chamber 71 0 is limited by a substrate 730.
  • the holding chamber 740 is an annular shape circumfering the transparent chamber 710 but might be a different shape. Its external diameter is up to about 10 mm leaving some room for supporting member 705 to support the lens inside the eye.
  • At the location of the holding chamber at the substrate there are electronic components 780 of the adjustable optic to
  • the internal surface of the holding chamber 740 includes conductive coating (Au, T1O2, etc.) 760 and 770 coated with protective coatings for their protection from the optical fluid. It also could be a wiring to form a conducting surface.
  • the coating 760 is placed on the flexible membrane 750 of the holding chamber. Together, the conductive coatings 760 and 770 act as electrodes to form electrostatic chamber with a dialectic material such as protective coatings and optical fluid between them.
  • the Figure 1 demonstrates the adjustable lens for far focus when the voltage is not applied to electrodes 760 and 770 and the holding chamber is in the relaxed state.
  • FIG. 1 1 demonstrates the adjustable lens 700' from Figure 10 in active state for near focus.
  • the electronic component 780 receives a signal corresponding to accommodation and turns on the voltage between electrodes 760' and 770.
  • An electrostatic force between the conductive surfaces of the electrostatic chamber is created when a voltage is applied between the electrodes,
  • the electronic component 780 As the electronic component 780 receives a signal corresponding to disaccommodation, it turns the voltage off to bring the transparent chamber shape to the configuration for far focus shown on the Figure 10.
  • the signal from a sensor cell might also be in analog form to continually control the dual-chamber fluidic lens shape, i.e. to continue increasing the optical power to certain level corresponding to a level of the signal from the censor cell that, in turn, is the result of a certain level of the ciliary muscle activity.
  • the central point of the Figures 1 0 and 1 1 is that dual- chamber fluidic lens allows a practical implementation of such a control.
  • FIG. 12 demonstrates dual-chamber fluidic adjustable optic of intraocular lens 800 shaped for a typical aphakic implantation with additional, so called control chamber 910 to indirectly effect the shape of the holding chamber 840. Similar to Figure 10, it includes transparent chamber 810 that effects the optical power of the lens due a change in its shape by the elastic membrane 820 and holding chamber 840 which shape is controlled by the shape of elastic membrane 850. Transparent and holding chambers are filled with an optical fluid.
  • the transparent chamber 81 0 is within the optical aperture of the lens, about 4-6 mm diameter, i.e. image forming part of the lens.
  • the other side of the transparent chamber 810 is limited by a substrate 830.
  • the holding chamber 840 is an annular shape circumfering the transparent chamber 810 but might be a different shape. Its external diameter is up to about 10 mm.
  • electronic components 880 of the adjustable optic to communicate with the sensor cell and activate optic for an optical power change.
  • control chamber 910 There is a control chamber 910 surrounded by conductive coatings 860 and 870 acting as electrodes of electrostatic chamber.
  • the conductive coating 870 is on non-elastic wall 890 and conductive coating 860 is on the elastic membrane 850 separating control chamber 910 and holding chamber 840.
  • elastic membrane 900 There is also elastic membrane 900, as a continuation of wall 890 in this case to form so called excess chamber 920. Excess chamber 920 and control chamber 910 form a single chamber but they might be separated by a channel.
  • the adjustable lens 800 is shaped for near focus in the resting state when the voltage is not applied to the electrostatic chamber
  • FIG. 13 demonstrates the adjustable lens 800' of Figure 12 in active state for far focus.
  • the electronic component 880 receives a signal corresponding to disaccommodation and turns on the voltage between conductive coatings 860' and 870. Due to attraction between the conductive coatings, the flexible membrane 850' deforms reducing the volume of the control chamber 91 0' and increasing the volume of the holding chamber 840' thus transporting a certain amount of optical fluid from the transparent chamber 810' to the holding chamber 840' by flattening membrane 820'. The result is lower optical power of adjustable lens 800' for far focus.
  • the reduced volume of the control chamber 910' forces some amount of dielectric fluid into the excess chamber 920' by deforming the elastic membrane 900'.
  • FIG. 14 demonstrates the adjustable lens designed for far focus in the relaxed state, i.e. in absence of power (voltage). In addition, it overcomes a need for adjustable optic voltage calibration for required Add power because tolerances of membranes of different chambers involved.
  • the optic shown on the Figure 14 is switchable optic in which the difference between far and near foci, i.e. Add power, is inherently established by the adjustable optic itself.
  • the U.S. Patent Applciation Publication No: 2014/0085726 introduced refractive-diffractive switchable (RDS) optical element that acts as opto-mechanical transistor for switching between near and far foci if a pressure is above certain level or below certain level.
  • RDS refractive-diffractive switchable
  • An RDS optic 1000 of the present invention includes substrate 1030 with diffractive guiding surface 1060 to set the Add power of the RDS optic.
  • the lens includes elastic film 1070 adjacent of the guiding surface to form transparent chamber between the film 1070 and guiding surface 1060 filled with matching optical fluid.
  • the transparent chamber is connected with holding chamber 1040 by channel 1080.
  • the holding chamber 1040 and control chamber 1010 are separate by the elastic membrane 1050, otherwise they are surrounded by non-elastic walls.
  • Internal surfaces of the control chamber 1 010 are coated with conductive coatings 960 and 970 which are also coated by protective coating for their protection from the dielectric fluid between them.
  • the conductive coatings 960 and 970 act as electrodes to form electrostatic chamber.
  • the control chamber 1010 is also connected with the excess chamber 1020 by the channel 1070. There is a power source 1090 for the electrodes 960 and 970 controlled by electronic components of the RDS lens 1 000. In the absence of voltage, the control chamber 1010, holding chamber 1040 and transparent chamber are all in equilibrium with resting state of the elastic film 1070 with the film 1070 forming refractive surface for far focus.
  • FIG. 15 demonstrates the adjustable optic 1000' of the Figure 14 in active state for near focus.
  • the electronics of the adjustable optic 1000' receives a signal to switch to higher power for near focus and activates power source 1090 to apply voltage between conducting coatings 960' and 970 of the control chamber 1010'. Due to attracting force between the electrodes 960 and 970, the flexible membrane 1050' deforms thus increasing the volume of the holding chamber 1040'. The balance of dielectric fluid of the control chamber 1010' is pushed into the excess chamber 1 020' via the channel 1070.
  • the holding chamber 1 040' volume increases, it pulls in certain amount of matching fluid from the transparent chamber between the guiding surface 1 060 and elastic film 1070 via the channel 1080 forcing the film 1070' takes largely the shape of the guiding surface 1 060 to manifest the equivalent diffractive surface shape for near focus.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Public Health (AREA)
  • Animal Behavior & Ethology (AREA)
  • Veterinary Medicine (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • General Health & Medical Sciences (AREA)
  • Molecular Biology (AREA)
  • Biophysics (AREA)
  • Surgery (AREA)
  • Ophthalmology & Optometry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Medical Informatics (AREA)
  • Pathology (AREA)
  • Physics & Mathematics (AREA)
  • Cardiology (AREA)
  • Dentistry (AREA)
  • Physiology (AREA)
  • Transplantation (AREA)
  • Vascular Medicine (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Prostheses (AREA)

Abstract

La présente invention concerne un système d'adaptation optique destiné à un œil et comporte un ensemble capteur et un ensemble optique réglable. L'ensemble capteur comporte un capteur, conçu de façon à détecter un mouvement du muscle ciliaire et à produire un signal ; un processeur électronique ; un émetteur et une source d'alimentation. L'ensemble optique réglable est conçu de façon à être soit implanté dans ou sur l'œil, soit disposé de manière adjacente à l'œil ou à proximité de ce dernier. L'ensemble optique réglable comporte un ensemble lentille optique commutable, conçu de façon à modifier sa puissance optique entre un premier état et un second état ; un récepteur, conçu de façon à recevoir le signal transférable provenant de l'émetteur de l'ensemble capteur ; un second processeur électronique connecté au récepteur, qui dirige l'ensemble lentille optique commutable afin de modifier sa puissance optique entre le premier état et le second état ; et une seconde source d'alimentation, connectée au second processeur électronique.
PCT/US2015/019781 2014-03-11 2015-03-10 Système optique sans fil de correction de la presbytie WO2015138507A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP15762170.7A EP3116443A4 (fr) 2014-03-11 2015-03-10 Système optique sans fil de correction de la presbytie

Applications Claiming Priority (8)

Application Number Priority Date Filing Date Title
US201461950942P 2014-03-11 2014-03-11
US61/950,942 2014-03-11
US201461984954P 2014-04-28 2014-04-28
US61/984,954 2014-04-28
US201462027123P 2014-07-21 2014-07-21
US62/027,123 2014-07-21
US14/642,236 US9931203B2 (en) 2011-08-02 2015-03-09 Presbyopia correcting wireless optical system
US14/642,236 2015-03-09

Publications (1)

Publication Number Publication Date
WO2015138507A1 true WO2015138507A1 (fr) 2015-09-17

Family

ID=54072345

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2015/019781 WO2015138507A1 (fr) 2014-03-11 2015-03-10 Système optique sans fil de correction de la presbytie

Country Status (2)

Country Link
EP (1) EP3116443A4 (fr)
WO (1) WO2015138507A1 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2017191542A1 (fr) 2016-05-02 2017-11-09 Gilad Barzilay Lentille intraoculaire et procédés et/ou composants associés à cette lentille intraoculaire
WO2018004831A1 (fr) * 2016-06-27 2018-01-04 Verily Life Sciences Llc Dispositif intraoculaire avec électronique auxiliaire couplée sans fil
EP3491458A4 (fr) * 2016-07-27 2020-03-18 Elwha LLC Dispositifs ophtalmiques et procédés correspondants
WO2021123258A1 (fr) 2019-12-20 2021-06-24 Carl Zeiss Meditec Ag Système de lentille intraoculaire, lentille intraoculaire et implant de corps ciliaire

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20130035760A1 (en) * 2011-08-02 2013-02-07 Valdemar Portney Switchable diffractive accommodating lens
US20130164815A1 (en) * 1999-11-13 2013-06-27 Grifols, S.A. Process for the production of a reversibly inactive acidified plasmin composition
US20130190867A1 (en) * 2005-10-27 2013-07-25 Gholam A. Peyman Adjustable fluidic telescope
US20130194540A1 (en) * 2012-01-26 2013-08-01 Randall Braxton Pugh Ophthalmic lens assembly having an integrated antenna structure
US20130245754A1 (en) * 2010-11-15 2013-09-19 Elenza Inc. Adaptive intraocular lens
US20130282117A1 (en) * 2012-04-23 2013-10-24 Anthony Van Heugten Systems, Devices, and/or Methods for Managing Implantable Devices

Family Cites Families (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9016860B2 (en) * 2005-10-27 2015-04-28 Gholam A. Peyman Fluidic adaptive optic fundus camera
EP2328515B1 (fr) * 2008-07-03 2017-12-06 Elenza, Inc. Capteur pour détecter un déclencheur d accommodation
US9241669B2 (en) * 2012-07-18 2016-01-26 Johnson & Johnson Vision Care, Inc. Neuromuscular sensing for variable-optic electronic ophthalmic lens

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20130164815A1 (en) * 1999-11-13 2013-06-27 Grifols, S.A. Process for the production of a reversibly inactive acidified plasmin composition
US20130190867A1 (en) * 2005-10-27 2013-07-25 Gholam A. Peyman Adjustable fluidic telescope
US20130245754A1 (en) * 2010-11-15 2013-09-19 Elenza Inc. Adaptive intraocular lens
US20130035760A1 (en) * 2011-08-02 2013-02-07 Valdemar Portney Switchable diffractive accommodating lens
US20130194540A1 (en) * 2012-01-26 2013-08-01 Randall Braxton Pugh Ophthalmic lens assembly having an integrated antenna structure
US20130282117A1 (en) * 2012-04-23 2013-10-24 Anthony Van Heugten Systems, Devices, and/or Methods for Managing Implantable Devices

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP3116443A4 *

Cited By (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2017191542A1 (fr) 2016-05-02 2017-11-09 Gilad Barzilay Lentille intraoculaire et procédés et/ou composants associés à cette lentille intraoculaire
CN109069266A (zh) * 2016-05-02 2018-12-21 G·巴尔齐莱 人工晶状体和与之相关的方法和/或组件
EP3451971A4 (fr) * 2016-05-02 2020-01-01 Gilad Barzilay Lentille intraoculaire et procédés et/ou composants associés à cette lentille intraoculaire
US10835374B2 (en) 2016-05-02 2020-11-17 Gilad BARZILAY Intraocular lens and methods and/or components associated therewith
CN109069266B (zh) * 2016-05-02 2021-09-21 G·巴尔齐莱 人工晶状体和与之相关的方法和/或组件
WO2018004831A1 (fr) * 2016-06-27 2018-01-04 Verily Life Sciences Llc Dispositif intraoculaire avec électronique auxiliaire couplée sans fil
US10076408B2 (en) 2016-06-27 2018-09-18 Verily Life Sciences Llc Intraocular device with wirelessly coupled auxiliary electronics
EP3692949A1 (fr) * 2016-06-27 2020-08-12 Verily Life Sciences LLC Dispositif intraoculaire avec système électronique auxiliaire à couplage sans fil
US10820987B2 (en) 2016-06-27 2020-11-03 Verily Life Sciences Llc Intraocular device with wirelessly coupled auxiliary electronics
US11364109B2 (en) 2016-06-27 2022-06-21 Verily Life Sciences Llc Intraocular device with wirelessly coupled auxiliary electronics
EP3491458A4 (fr) * 2016-07-27 2020-03-18 Elwha LLC Dispositifs ophtalmiques et procédés correspondants
WO2021123258A1 (fr) 2019-12-20 2021-06-24 Carl Zeiss Meditec Ag Système de lentille intraoculaire, lentille intraoculaire et implant de corps ciliaire

Also Published As

Publication number Publication date
EP3116443A4 (fr) 2017-12-06
EP3116443A1 (fr) 2017-01-18

Similar Documents

Publication Publication Date Title
US9931203B2 (en) Presbyopia correcting wireless optical system
AU2017202009B2 (en) Neuromuscular sensing for variable-optic electronic ophthalmic lens
US20200397565A1 (en) Electromyographic sensing and vision modification
US9226818B2 (en) Sensors for triggering electro-active ophthalmic lenses
US10285803B2 (en) Inductive coil sensor for vision corrective apparatus and methods therefor
JP6133294B2 (ja) プロセッサ制御された眼内レンズシステム
EP2328515B1 (fr) Capteur pour détecter un déclencheur d accommodation
AU2013209924B2 (en) Accommodating intra-ocular lens system
WO2015138507A1 (fr) Système optique sans fil de correction de la presbytie
WO2013059656A2 (fr) Procédés et appareil pour détecter des éléments déclencheurs d'accommodation
US10980630B1 (en) Contact lens-based methods to deliver power to intraocular devices
CN111201468B (zh) 电润湿透镜的电压驱动器
TW201900100A (zh) 用於睫狀肌振動偵測的系統及方法
US20060136055A1 (en) Pseudoaccommodative equipment implanted for presbyopia correction
CN109414318A (zh) 具有无线耦合辅助电子设备的眼内设备
US20210393957A1 (en) Systems and Methods for Sensing and Correcting Electrical Activity of Nerve Tissue
CN111970969A (zh) 具有肌肉传感器的眼部可安装设备
US20180173013A1 (en) Electrode configuration for sensing ciliary impedance
Barrettino Look into my eyes
US20180085212A1 (en) Ocular function assistance device
TW201836545A (zh) 用於眼用裝置之阻抗感測電路

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 15762170

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

REEP Request for entry into the european phase

Ref document number: 2015762170

Country of ref document: EP

WWE Wipo information: entry into national phase

Ref document number: 2015762170

Country of ref document: EP