WO2021180693A1 - Lentille oculaire artificielle - Google Patents

Lentille oculaire artificielle Download PDF

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Publication number
WO2021180693A1
WO2021180693A1 PCT/EP2021/055874 EP2021055874W WO2021180693A1 WO 2021180693 A1 WO2021180693 A1 WO 2021180693A1 EP 2021055874 W EP2021055874 W EP 2021055874W WO 2021180693 A1 WO2021180693 A1 WO 2021180693A1
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WO
WIPO (PCT)
Prior art keywords
liquid
energy
compartment
eye lens
eye
Prior art date
Application number
PCT/EP2021/055874
Other languages
German (de)
English (en)
Inventor
Mario Gerlach
Original Assignee
Carl Zeiss Meditec Ag
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 Carl Zeiss Meditec Ag filed Critical Carl Zeiss Meditec Ag
Priority to EP21710957.8A priority Critical patent/EP4117578A1/fr
Publication of WO2021180693A1 publication Critical patent/WO2021180693A1/fr

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Classifications

    • 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
    • A61F2/1648—Multipart lenses
    • 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
    • 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
    • A61F2/1629—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 longitudinal position, i.e. along the visual axis when implanted
    • 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
    • A61F2/1632—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 radial position, i.e. perpendicularly to the visual axis when implanted
    • 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
    • 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
    • A61F2/1637—Correcting aberrations caused by inhomogeneities; correcting intrinsic aberrations, e.g. of the cornea, of the surface of the natural lens, aspheric, cylindrical, toric lenses
    • A61F2/1645—Toric lenses
    • 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
    • A61F2/1654—Diffractive lenses
    • A61F2/1656—Fresnel lenses, prisms or plates

Definitions

  • the present invention relates to an eye lens with a haptic element and an optical element, the optical element having at least two optical surfaces.
  • the invention further relates to a planning unit for generating control data for a correction device to improve the visual performance of an eye which has an eye lens according to the invention, the correction device having an energy device for providing energy, a focusing device for focusing the energy in an energy focus, and a control unit Control of the correction device by means of the control data comprises, the planning unit having an interface for transferring the control data to the control unit.
  • the invention also relates to a corresponding correction device.
  • the invention relates to a planning method for generating control data for a correction device and a method for improving the visual performance of an eye.
  • Intraocular lenses are artificial eye lenses made from a transparent material. They can be implanted in the eye instead of or in addition to the natural lens of the eye, for example to correct the refractive power (often also referred to as the refractive power) of a myopic, hyperopic or astigmatic eye.
  • the vision of a diseased eye can be improved or restored, for example in the case of cataract disease.
  • the term vision should be understood to mean the quality of a scene perceived with one eye, which can be impaired, for example, by lens opacity, astigmatism, decentering of the optically effective surfaces, but also by non-adapted refractive powers.
  • the eye Before an intraocular lens is implanted, the eye is typically measured in order to determine the required refractive power depending on, for example, the eye length, the curvature of the cornea and the planned position of the artificial eye lens in the capsular bag. In this way it can be used for the overall optical system of the eye, in addition to the artificial Eye lens, for example, also includes the cornea, achieve a desired total refractive power.
  • the eye is an organic tissue whose (mechanical) properties can change as a result of the intervention during implantation and / or during the subsequent wound healing, it can happen that the position of the implanted eye lens is shifted or twisted, or that the refractive power of the eye lens does not lead to the desired, calculated improvement in the vision of the eye.
  • DE 101 05080 B4 proposes an eye lens with a haptic which has an adjusting device with the aid of which the lens can be axially displaced using a tool after the implantation (and wound healing). This requires a new, invasive surgical procedure with the associated health risks. Furthermore, an operating room (OR) is required for this procedure and is therefore associated with considerable expense.
  • WO 03/057022 A1 describes an eye lens whose optical properties can be changed by an external stimulus after implantation.
  • the lens comprises light-sensitive polymers that absorb light or heat and thereby change their refractive index or the curvature of the lens.
  • the implant Due to the light sensitivity of the lens material - also to daylight - the patient has to wear UV protective goggles for several weeks after the wound has healed, the implant has stabilized in the capsular bag and the lock-in, in order to prevent the properties of the implanted eye lens from being unintentionally changed change. After the lock-in there is none further correction of the lens more possible.
  • a correction of the proposed eye lens requires a special therapy planning and radiation device and is therefore associated with additional costs for the doctor.
  • WO 2014/077983 describes an eye lens and a device which make it possible to change the refractive index of the lens by irradiation with a pulsed laser with a pulse duration in the range of femtoseconds (fs laser).
  • fs laser femtoseconds
  • hydrophilic lens material is exposed to laser pulses below the damage threshold in order to locally change the water content.
  • the method is limited to hydrophilic eye lenses and, on the other hand, it requires a special device which is very expensive due to the required fs laser and the use in an operating room.
  • US 2014/0200666 A1 presents an eye lens with a haptic, in which a toric lens is rotatably coupled to the haptic.
  • the lens is held against the haptic by means of fastenings that are subject to tensile force. After the implantation (and the wound healing), some fastenings can be severed with the help of a laser so that the lens rotates in relation to the haptic, for example to correct an astigmatism.
  • the disadvantage of the solution described is that the correction can only take place in very few, discrete steps and is only reversible to a limited extent.
  • the visual performance of an eye in which an artificial lens is implanted can be impaired not only by reduced vision, but also by a disease.
  • the term “visual performance” includes not only the optical properties of the eye, such as refractive power and transmission, which affect vision, but also other properties of the eye that affect the retina, for example.
  • a condition that affects visual performance such as wet age-related macular degeneration (AMD) is often treated with an injection through the eyeball (sclera) into the eye. Such injections are for the Patients very painful and carry the risk of infection and thus complete loss of visual performance.
  • AMD wet age-related macular degeneration
  • a first aspect of the invention relates to an eye lens that has a haptic element and an optical element.
  • the haptic element is designed to be fixed in the eye, preferably in the capsular bag or on the ciliary sulcus.
  • the optical element can be shaped, for example, as a plate haptic or a C-loop haptic.
  • the optical element has at least two optical surfaces. These can be refractive or diffractive and applied to any basic shape (e.g. spherical, aspherical, toric, Fresnel structure or freeform surface).
  • the eye lens is characterized in that it furthermore comprises a compartment which is designed to receive a liquid.
  • the compartment has an outlet channel with an outlet valve.
  • the outlet valve is designed to allow the liquid to flow out of the compartment through the outlet channel and to block the liquid from flowing into the compartment through the outlet channel.
  • the compartment has an inlet channel with an inlet valve.
  • the inlet valve is designed to allow the liquid to flow into the compartment through the inlet channel and to block the liquid from flowing out of the compartment through the inlet channel.
  • the fluid can enter the compartment through the inlet channel during or after the implantation; it can also be at the time of the Implantation fluid located in the compartment that has entered the compartment via the inlet channel.
  • the eye lens is designed to allow energy to be introduced into the liquid taken up in the compartment.
  • the transmission for the energy of the energy input through the compartment can be at least 50%, preferably at least 90%, particularly preferably at least 95%.
  • Part of the energy of the energy input can be absorbed by the liquid absorbed into the compartment.
  • the local intensity that occurs can generate a very hot plasma of more than 10,000K and thus a rapidly expanding gas bubble made of liquid vapor.
  • the pressure can rise to more than 20 bar, for example. Due to its space occupation and the associated pressure increase, the gas bubble can displace the surrounding liquid and, on the one hand, lead to the expansion of the surrounding compartment (within the scope of its elasticity).
  • a metered delivery of the liquid through the outlet channel and the outlet valve from the compartment can take place. An outflow through the inlet channel is prevented by the inlet valve.
  • a dosed portion of the liquid taken up in the compartment can thus be released through the exit channel as a result of the energy input.
  • the dose delivered can depend on the material properties of the liquid (e.g. absorption for the energy form of the energy input) and the compartment (e.g. elasticity), the mechanical properties of the outlet valve (e.g. closing force), the shape of the outlet channel (via the frictional forces), the pressure conditions in the compartment and beyond the output channel and / or depend on the amount of energy and energy duration of the energy input. This can be simulated or determined experimentally.
  • the gas bubble in the compartment can collapse again and release the mass again.
  • the compartment returns to its original size.
  • the input channel and The inlet valve allows liquid to flow into the compartment until equilibrium has been established again. An inflow through the outlet channel is prevented by the outlet valve.
  • the lens of the eye After fluid flows back into the compartment, the lens of the eye is ready for a renewed input of energy and a renewed, metered release of fluid.
  • the dosed delivery can therefore be repeated.
  • the dose amount can be adjusted via the size of the energy input.
  • the eye lens can also be designed for thermal energy input and / or pulsed energy input.
  • the eye lens according to the invention allows a metered, microfluidic transport of a liquid or a liquid displacement in the implanted eye.
  • a hydraulic effect is used here.
  • the fluid displacement is made possible by the “micropump” encompassed by the lens of the eye, which can be controlled from the outside via an energy input.
  • the visual performance of the implanted eye can advantageously be improved non-invasively, for example via a hydraulic change in the optical properties of the optical element or by dispensing a medicament.
  • the eye lens according to the invention advantageously provides a practically stepless pump output as often as desired and as long as desired after the implantation.
  • the eye lens is designed in such a way that the compartment has an absorber which is designed to at least partially absorb the energy input and to give it off in the form of heat to the liquid taken up in the compartment.
  • an absorber which is designed to at least partially absorb the energy input and to give it off in the form of heat to the liquid taken up in the compartment.
  • the absorber can have magnetic properties so that energy can be introduced via induction. The absorber can then transfer the resulting heat to the liquid in the compartment.
  • Materials with a high density for example, are suitable as absorbers for the energy form ultrasound.
  • the eye lens is designed in such a way that the dosed release of the liquid from the compartment is made possible by an energy input into the liquid via a laser pulse.
  • the space-occupying element can be created by a laser-induced cavitation bubble within the compartment.
  • the space-occupying element can be generated thermally and / or by pulsed laser excitation.
  • the areas of the optical element and / or the haptic element as well as the areas of the compartment through which the laser pulse can radiate to generate the energy input are designed in such a way that they have a high transmission.
  • the transmission for the wavelengths of the laser pulse can be at least 50%, preferably at least 90%, particularly preferably at least 95%.
  • the wavelengths can, for example, be in the range of visible light or in the infrared range.
  • the absorber in the compartment allows particularly efficient thermal energy input.
  • the absorber can be colored in the spectral range of the laser light.
  • the absorber can be transparent; this is particularly advantageous in the case of an absorber for infrared light, since the absorber cannot be perceived as disturbing by either the implanted eye or the outside.
  • the compartment and outlet channel are designed in such a way that the dosed release of the liquid from the compartment is made possible by energy input into the liquid via a laser pulse with a pulse energy between 500 pJ and 5 mJ.
  • the laser pulse can be generated, for example, by an Nd: YAG laser, the laser beam of which is focused into the liquid-filled compartment. This laser pulse transports the energy required for the energy input within a pulse duration of a few nanoseconds.
  • Nd YAG lasers are used, for example, in a capsulotomy.
  • the specifications of such a laser are outstandingly suitable for use with the eye lens according to the invention.
  • Such lasers are available in very large numbers in clinical practice and are easy to use.
  • no expensive purchases are necessary.
  • no special material modifications are required; Rather, commercially available materials can be used for the eye lens, since they have the required transmission properties.
  • the inlet valve and / or the outlet valve is a flutter valve, a ball valve, a cone valve or a diaphragm valve.
  • valve types mentioned have in common that they can also be manufactured in a small size required for use in an eye lens and from materials that are customary in medical technology, for example because of their biocompatibility.
  • the haptic element is arranged to be movable with respect to the optical element.
  • the eye lens also has a displacement device along which the optical element can be moved relative to the haptic element.
  • the displacement device can be part of the haptic element or the optical element be. It can also be designed in two or more parts.
  • a displacement device part can be part of the haptic element and / or the optical element.
  • the displacement device has a reservoir which is designed to receive liquid. The reservoir is connected to the outlet channel of the compartment in such a way that the liquid can be discharged from the compartment via the outlet channel and through the outlet valve into the reservoir.
  • the reservoir is connected to the inlet channel in such a way that the liquid can be discharged from the reservoir through the inlet valve via the inlet channel into the compartment.
  • the lens of the eye preferably has at least two compartments; one compartment is connected to the reservoir via its outlet channel and another compartment is connected to its inlet channel.
  • the reservoir is designed in such a way that, in the event of a change in volume, a change in position of the optical element relative to the haptic element along the displacement device is made possible by a metered delivery of the liquid into the reservoir or out of the reservoir.
  • the displacement device can for example have a rail, a groove or a thread. It makes it possible to define the direction in which a relative change in position between the haptic element and the optical element is to take place.
  • the displacement device and the valves are preferably designed in such a way that a displacement between the optical element and the haptic element already takes place at a lower pressure than the opening of a valve.
  • the change in position can be, for example, a shift.
  • a shift between the optical surfaces of the eye lens and the optically effective surfaces of the eye (such as the cornea) can be achieved.
  • this enables decentering errors to be reduced and thus an improvement in the visual performance of the eye via an improvement in vision.
  • the focal length of the entire eye can be adjusted and thus improve the visual acuity by improving the image sharpness on the retina.
  • the change in position can also be a rotation, for example. If one of the optical surfaces of the optical element has a toric shape, an astigmatism of the eye can be corrected by rotating the optical element with respect to the haptic element (and thus with respect to the optically active surfaces of the eye) and thus improve the eyesight.
  • the eye lens enables a non-invasive correction of the vision of an eye with an implanted artificial eye lens, which can be carried out at any point in time and practically continuously.
  • the optical element has an optical axis.
  • the optical axis can be defined, for example, via the connection of the lens vertices of two optical surfaces of the optical element.
  • the haptic element and the optical element are advantageously designed in such a way that the optical axis of the optical element is parallel to the optical axis of the eye in the implanted state of the eye lens.
  • the displacement device is advantageously designed to enable the change in position of the optical element with respect to the haptic element perpendicular to the optical axis, parallel to the optical axis and / or rotating about the optical axis.
  • a change in the position of the optical element with respect to the haptic element perpendicular to the optical axis of the optical element advantageously allows the two optical axes of the optical element and eye to be pushed over one another. In this way, aberrations due to decentering errors can be corrected particularly well and thus the eyesight can be improved.
  • a change in position of the optical element with respect to the haptic element parallel to the optical axis of the optical element advantageously allows distances between optically effective surfaces such as the cornea and the optical surfaces of the optical element to be adapted. In this way, the vision of the entire eye can be improved via the resulting change in focus position.
  • a rotational change in position of the optical element with respect to the haptic element around the optical axis of the optical element advantageously allows the axial position of a toric optical element to be changed and thus the astigmatism of the implanted eye to be corrected particularly well.
  • the haptic element has at least two optical surfaces. In the implanted state, these surfaces can be used together with the optical surfaces of the optical element to guide the imaging light onto a retina of the eye.
  • the optical surfaces of the haptic element can be refractive or diffractive and applied to any basic shape (e.g. spherical, aspherical, toric, Fresnel structure or freeform surface).
  • the eye lens thus has at least four optical surfaces.
  • optical axes of the optical surfaces of the haptic element and the optical element are advantageously parallel.
  • a change in the position of the optical element with respect to the haptic element then allows the two optical axes to be placed one above the other. In this way, aberrations due to decentering errors can be corrected and eyesight improved.
  • One of the optical surfaces of the haptic element and the optical element can have a toric shape.
  • An optical surface of the optical element advantageously has a toric shape.
  • an optical surface of the haptic element can have a toric shape.
  • a rotational relative movement of the optical element with respect to the haptic element then advantageously allows the axial position of the toric optical element to be changed (possibly with respect to the axial position of an optical surface of the haptic element) and thus a coordination of the axial position for astigmatic ones Make corrections. In this way, astigmatic imaging errors caused by the axis position can be corrected and eyesight improved.
  • the optical axes of the optical element and the optical area of the haptic element are advantageously identical.
  • the higher number of optical surfaces increases the number of parameters such as lens curvature, refractive index or Abbe number, which are available for improving the vision of an implanted eye. It also allows a further improvement in the correction of remaining chromatic errors.
  • At least one of the optical surfaces of the haptic element and the optical element can each be designed as a third-order freeform surface according to Lohmann or Alvarez.
  • the design of such surfaces is adequately described in the technical literature and is not the subject of the invention.
  • a lateral or rotational, relative change in position of the haptic element and the optical element advantageously allows an adaptation of the refractive power and can thus improve the vision of the implanted eye post-operatively.
  • the haptic element also has optical surfaces (such as free-form surfaces according to Lohman or Alvarez), the refractive power can be reversibly adapted. In the case of a rotary movement of a toric optic, the maximum required adjustment angle can be reduced (from up to 180 ° to up to 90 °).
  • An eye lens with at least two compartments can also have a second displacement device along which the optical element is opposite the haptic element can be moved.
  • the second displacement device comprises a second reservoir which is designed to receive the liquid.
  • the second reservoir is connected to the outlet channel of the second compartment in such a way that the liquid can be discharged from the second compartment via the outlet channel and through the outlet valve into the second reservoir, or the second reservoir is connected to the inlet channel in such a way that the Liquid can be dispensed from the second reservoir through the inlet valve via the inlet channel into the second compartment.
  • the angle between the changes in position is preferably between 80 ° and 100 °. In this way, for example, any displacements between the optical axis of the optical element and the eye can be corrected or a lateral displacement of the optical axis of the optical element and an additional axial displacement can be achieved.
  • the optical element is shaped as a liquid lens, which is designed to take up liquid in a liquid space.
  • the liquid lens has at least two further optical surfaces.
  • the liquid lens thus comprises at least four optical surfaces.
  • At least one of the at least four optical surfaces of the liquid lens is designed in such a way that a change in the refractive index of the optical element can be generated by changing the volume of the liquid in the liquid space.
  • at least one optical surface can change its curvature, for example.
  • the liquid space is connected to the outlet channel of the compartment in such a way that the liquid can be discharged from the compartment via the outlet channel and through the outlet valve into the liquid space.
  • a release of liquid from the compartment into the liquid space leads to a change in volume there; this in turn leads to a change in the refractive power.
  • the liquid space is connected to the inlet channel of a further compartment (different from the first compartment) in such a way that the liquid can be discharged from the liquid space through the corresponding inlet valve via the inlet channel into the further compartment.
  • the change in the refractive index is made possible by the change in volume of the liquid in the liquid space when the liquid is dispensed in a metered manner into the liquid space or out of the liquid space.
  • the eye lens according to the invention thus allows the refractive power of the eye lens to be changed or corrected in the event of an energy input into the compartment and a resulting dosed release of liquid in order to improve the vision of the eye post-operatively.
  • the eye lens enables a non-invasive correction of the vision of the implanted eye, which can be carried out at any point in time and practically continuously.
  • At least two optical surfaces of the liquid lens are advantageously designed to change their curvature when there is a change in volume in the liquid space.
  • This can apply, for example, to the pair of surfaces from the front side and the inner surface of the front side and / or to the pair of surfaces from the rear side and the inner surface of the rear side.
  • the material between the pairs of surfaces mentioned can be designed to be flexible, for example as a membrane.
  • the pair of surfaces can have a fixed distance, preferably at a Change in curvature remains constant (apart from a slight change due to stretching of the material).
  • the distance can also be different across the surfaces (but remain constant with a change in curvature); the distance preferably changes radially, for example the distance between the pairs of surfaces decreases with increasing radius.
  • the liquid that is transported into or out of the liquid space via the microfluidic pump according to the invention can be aqueous humor or a physiological saline solution or comprise these.
  • a pair of surfaces has a spatially non-constant distance, since this increases a change in the refractive power when the curvature changes.
  • It can also be a liquid that has a refractive index that deviates from the refractive index of the aqueous humor (and is preferably greater). In this way, a change in the refractive power can be amplified when the curvature changes.
  • the liquid is preferably kept in a closed system.
  • the channel of the compartment which is not connected to the liquid space of the liquid lens, can be connected to a liquid storage space. In this way, the liquid remains in the liquid storage space, in the compartment or in the liquid space regardless of a liquid transport.
  • the eye lens the optical element of which comprises a liquid lens
  • the inlet channel of one compartment and the outlet channel of another compartment are connected to the liquid space.
  • the two channels of the compartments that are not connected to the liquid space can be connected to a single liquid storage space or also each with a liquid storage space.
  • the liquid comprises a physiological salt solution (also called “balanced salt solution” or BSS), aqueous humor and / or a medicinal agent.
  • BSS physiological salt solution
  • aqueous humor and / or a medicinal agent.
  • BSS balanced salt solution
  • aqueous humor and / or a medicinal agent.
  • a liquid whose refractive index differs from the refractive index of aqueous humor.
  • the visual performance of the implanted eye can also be improved via the dosed delivery of a medicinal substance.
  • a second aspect of the invention relates to a planning unit for generating control data for a correction device for improving the visual performance of an eye that has an eye lens according to one of the embodiments described above.
  • the correction device comprises an energy device for providing energy.
  • the energy device can be, for example, a light source such as a laser device. It can also be an ultrasound source or a magnetic field source that provides an alternating magnetic field in order to be able to provide energy input via induction.
  • the correction device comprises a focusing device for focusing the energy in an energy focus. This can be an optical system that is made up of one or more lenses, for example. It can also be a device that focuses ultrasound in one point.
  • the correction device has a control unit for controlling by means of the control data.
  • control unit is designed in such a way that it can transmit signal data, which are determined taking the control data into account, via a signal data line to the energy unit.
  • the control unit can be designed as a computer.
  • the planning unit preferably has an interface via which control data can be supplied to the control unit in a wired or wireless manner.
  • the planning unit is designed to generate additional control data with which the correction device can be controlled in such a way that the energy device provides the energy that enables energy to be introduced into the compartment of the eye lens, which enables the liquid to be dispensed in a dosed manner through the outlet channel and through the Output valve generated.
  • the further control data can be, for example, parameters for controlling the energy source, such as the amount of energy that is to be entered into the compartment, or the duration over which the entry is to take place, or a number of energy pulses.
  • the control data can be determined on the basis of previously determined information about the ametropia to be corrected or about the dose of the medical active ingredient to be delivered.
  • the control data can be determined taking into account information about the eye lens, for example the possible directions of movement between the flaptic element and the optical element (given by the guide device).
  • information about the relationship between a change in the position of the haptic element and the optical element and a change in the optical properties can be included in the calculations.
  • the planning unit can be designed as a computer which has a processor and a memory.
  • the planning unit can also be part of a computer which additionally comprises the control unit, for example.
  • the correction device is advantageously designed to shift the position of the energy focus in the eye lens. This can be achieved in that the (inherently rigid) unit of energy device and focusing device can be positioned freely movable in front of the eye; for this purpose, the unit can be designed as a hand-held applicator.
  • the correction device can have a chin and / or forehead support and / or a contact lens in order to position the eye with respect to the correction device.
  • the unit is then designed to be movable within the correction device in order to shift the energy focus in the eye lens.
  • the correction device can also have a deflection device which is arranged along an energy beam between the energy device and the focusing device. This allows the energy focus to be shifted in the lens of the eye.
  • the displacement device can be an optical deflection device such as, for example, a scanner. It can also be a device that can deflect an ultrasound focus. The deflection device and possibly also the focusing device allow the energy focus to be shifted three-dimensionally in the eye.
  • the planning unit can also generate control data which are converted by the control unit into signal data for the focusing device and / or the deflection device and which are passed on via corresponding signal data lines.
  • the planning unit according to the invention thus enables control data to be generated for a correction device which, when executed by the correction device, can improve the visual performance of an implanted eye post-operatively.
  • the planning unit according to the invention can generate the control data without the eye being connected to the correction device. Rather, the control data can be generated long before the correction is actually carried out.
  • the invention further relates to a correction device for improving the visual performance of an eye, which has an eye lens according to one of the above Has described designs.
  • the correction device has an energy device for providing energy, a focusing device for focusing the energy in an energy focus and a control unit for controlling the correction device by means of control data.
  • the correction device has a planning unit for generating the control data.
  • the planning unit is designed in such a way that it generates the control data as it is carried out in the embodiments described above.
  • the invention also relates to a planning method for generating control data for a correction device for improving the visual performance of an eye which has an eye lens according to one of the embodiments described above.
  • the correction device has an energy device for providing energy, a focusing device for focusing the energy in an energy focus and a control unit for controlling the correction device by means of the control data.
  • the planning method generates further control data with which the correction device can be controlled in such a way that the energy device provides the energy that enables the energy input in the compartment (30, 30.1) of the eye lens (1), which enables a metered delivery of the liquid through the outlet channel and generated by the outlet valve. Furthermore, the planning method includes a supply of the control data to the control unit of the correction device.
  • the invention further relates to a method for improving the visual performance of an eye, which has an eye lens according to one of the embodiments described above, with the aid of a correction device.
  • the correction device has an energy device for providing energy, a focusing device for focusing the energy in an energy focus and a control unit for controlling the correction device by means of control data.
  • the method comprises a step for generating further control data with which the correction device can be controlled in such a way that the energy device provides an energy that enables energy to be introduced into the compartment of the eye lens, which generates a metered delivery of the liquid through the outlet channel and through the outlet valve .
  • the method also includes supplying the control data to the control unit of the correction device.
  • the method has the step of entering energy in accordance with the control data into the compartment of the eye lens. For this purpose, the control data are converted into signal data in the control unit and transmitted to the energy device.
  • FIG. 1a shows a perspective illustration of a first exemplary embodiment of an eye lens according to the invention
  • FIG. 1b shows a perspective illustration of the exemplary embodiment of an eye lens according to the invention from FIG. 1a with an alternative haptic;
  • FIG. 1b shows a perspective illustration of the exemplary embodiment of an eye lens according to the invention from FIG. 1a with an alternative haptic;
  • 2a to 2d show a schematic representation of the functional principle of the transport of liquid through the input of energy; 3a to 3d schematic representations of various valves;
  • FIG. 4 shows a schematic representation of a compartment of a second exemplary embodiment of an eye lens according to the invention for the dosed release of a medicinal agent
  • 5 shows a plan view of a third exemplary embodiment of an eye lens according to the invention
  • FIG. 6 shows a plan view of a fourth exemplary embodiment of an eye lens according to the invention
  • 7a and 7b side views of an optical element for a fifth embodiment of an eye lens according to the invention for two different refractive values
  • FIG. 9 shows a schematic representation of a correction device.
  • the eye lens 1 comprises a flaptic element 20 and an optical element 10, which has a front side 12 facing the cornea in the implanted state and a rear side 14 facing the retina in the implanted state.
  • the eye lens 1 can be held or fixed in the capsular bag of the eye by means of the haptic 20.
  • the eye lens 1 can be introduced into an eye through a small incision.
  • the front side 12 and the rear side 14 of the optical element 10 are responsible for the optical imaging properties of the eye, its overall refractive power and for its vision due to their light-conducting properties in interaction with the other optically effective structures of the eye such as the cornea.
  • An optical axis A is shown as a dashed line as a connection between the lens vertices of the front side 12 and the rear side 14.
  • a perspective view is shown for a further embodiment. It differs from the embodiment in FIG. 1 a in that it has a different haptic element 20.
  • haptic element 20 In principle, otherwise shaped and configured haptic elements 20 can also be provided.
  • a haptic element 20 can also be provided which allows the eye lens 1 to be fixed in the ciliary sulcus.
  • FIGS. 2a to 2d show a schematic representation of the functional principle of the metered release of liquid through the input of energy.
  • the compartment 30 shown in the figures has an output channel 40 and an input channel 50.
  • a liquid 70 such as aqueous humor, is located in the compartment 30.
  • an outlet valve 45 is arranged, which allows liquid 70 to flow out of the compartment 30, but blocks it from flowing into it.
  • an input valve 55 is arranged in the input channel 50, which allows liquid 70 to flow into the compartment 30, but blocks an outflow out of it.
  • FIG. 2a energy is introduced with the aid of a laser pulse 60 (shown as a dotted arrow).
  • a plasma 72 is generated in the liquid 70 contained in the compartment 30 within a short period of time.
  • the expanding gas bubble 74 leads, on the one hand, to an expansion of the surrounding compartment 30 (not shown).
  • an outflow or expulsion of the surrounding liquid 70 through the outlet channel 40 and through the outlet valve 45 is caused.
  • the resulting liquid flow 80 is shown as a solid arrow.
  • An outflow of the liquid 70 through the inlet channel 50 is prevented by the inlet valve 55.
  • the gas bubble 76 collapses again (see FIG. 2c, the collapse is shown by eight inwardly directed arrows). This frees the space claim again.
  • the expanded compartment 30 compresses back to its original size.
  • liquid 70 flows through the inlet channel 50 and the inlet valve 55 into the compartment 30.
  • the liquid flow 80 is shown as a solid arrow. An inflow of liquid 70 through the outlet channel 40 is prevented by the outlet valve 45.
  • the compartment 30 After the gas bubble 76 has collapsed, the compartment 30 returns to a state of rest (FIG. 2d) in which there is no outflow or inflow of liquid 70. If more than just one dose of liquid 70 is to be dispensed, a renewed input of energy can take place.
  • a pulsed input of energy (for example with a pulsed laser) can also take place, which is matched to a resonance frequency of the compartment 30. A periodic and thus quasi-continuous pumping effect can be achieved through the repeated input of energy.
  • FIGS. 3a to 3d show schematic representations of various outlet valves 45 which can be used in compartment 30.
  • the exemplary embodiments are a flutter valve (FIG. 3a), a diaphragm valve (FIG. 3b), a ball valve (FIG. 3c) and a cone valve (FIG. 3d).
  • the respective valve is shown in broken lines in the open state and marked with the reference symbol 45 '. It goes without saying that the exemplary configurations shown for an output valve 45 can also be a configuration for an input valve 55.
  • the eye lens 1 additionally has an active ingredient compartment 100 with an active ingredient outlet channel 130 and an active ingredient outlet channel valve 135.
  • the active ingredient compartment 100 comprises an inlet which is connected to the outlet channel 40 of the compartment 30. Liquid 70 (when energy is introduced into compartment 30) can flow from compartment 30 into active ingredient compartment 100 via this inlet.
  • the active ingredient compartment 100 also has a membrane 120. The inlet to the active ingredient compartment 100 is separated from the active ingredient outlet channel 130 by the membrane in such a way that no liquid 70 can pass through the inlet to the active ingredient outlet channel 130.
  • the Active ingredient compartment 100 In the part of the Active ingredient compartment 100, which faces the active ingredient outlet channel 130, contains a liquid which comprises a medicinal active ingredient 110. If liquid 70 flows through the inlet into the active ingredient compartment 100, a pressure increase takes place there. This causes the membrane to move in a direction away from the entrance. This in turn results in a pressure increase in the liquid with the medicinal active substance 110; this increase in pressure is compensated for by means of a metered release of the medical active substance 110 through the active substance outlet channel 130 and the active substance outlet channel valve 135.
  • the active ingredient outlet channel valve 135 and the outlet valve 45 prevent the medical active ingredient 110 from flowing back into the active ingredient compartment 100 when the liquid 70 in the compartment 30 collapses (or cools).
  • the exemplary embodiment according to the invention thus allows post-operatively and non-invasively the dosed delivery of a medical active ingredient 110 into the eye;
  • the release takes place indirectly by pumping a liquid 70 into which an energy input takes place.
  • the medical active substance 110 which could possibly degenerate in the event of a direct energy input, remains unaffected by the energy input.
  • the exemplary embodiment shown is not restricted to the dosed delivery of a medicinal substance 110. Rather, another liquid can also be present as the liquid in the active ingredient compartment 100, which liquid could degenerate in the event of a direct input of energy and is therefore advantageously pumped indirectly. It can be a liquid for a liquid lens, for example.
  • the compartment 30 can also have a membrane 120.
  • the membrane 120 separates the first liquid 70 from a further liquid (such as, for example, one that comprises a medicinal substance 110).
  • a further liquid such as, for example, one that comprises a medicinal substance 110.
  • Fig. 5 is a plan view of a third embodiment of an eye lens 1 according to the invention is shown.
  • the flaptic element 20 is designed for implantation in the capsular bag or the ciliary sulcus and has the shape of a plate haptic.
  • the eye lens 1 has a displacement device which, in this exemplary embodiment, is designed in two parts:
  • the optical element 10 comprises an optically effective zone shown in a circle, which in the implanted state is suitable for imaging light guidance onto the retina of the eye, and is connected to a displacement device part 205 .
  • the second displacement device part 200 is connected to the haptic element 20 (shown as a dotted line).
  • the two-part displacement device 200, 205 allows a movement of the optical element 10 with respect to the haptic element 20 in a direction perpendicular to the optical axis (which protrudes from the plane of the drawing in the exemplary embodiment and is therefore not shown).
  • the possible shift directions are shown by a double arrow.
  • the displacement device also has a reservoir 210. This is connected to the output channel 40 of a compartment 30 and to the input channel 50 of a further compartment 30.1.
  • the black triangle in compartment 30 illustrates the possible direction in which liquid 70 can flow out of compartment 30; the tip of the triangle points to the outlet channel 40.
  • the exemplary embodiment thus shows an eye lens 1 which allows a lateral displacement of the optical element 10 in order, for example, to bring the optical axis A of the optical element 10 into alignment with the optical axis of the eye and thus to improve the eyesight.
  • the exemplary embodiment thus shows an eye lens 1 which allows reversible lateral displacement of the optical element 10.
  • FIG. 6 shows a plan view of a fourth exemplary embodiment of an eye lens 1 according to the invention.
  • the two displacement device parts 200 and 205 of the displacement device are designed in such a way that they allow a rotation of the optical element 10 relative to the flaptic element 20 about the optical axis A (not shown).
  • an energy input into the liquid of compartment 30 leads to an enlargement of the reservoir 210 and results in a clockwise rotation of the optical element 10 (with a fixed flaptic element 20).
  • an input of energy into the liquid of compartment 30.1 leads to a reduction in the size of the reservoir 210 and results in a counterclockwise rotation of the optical element 10 (when the flaptic element 20 is fixed).
  • the exemplary embodiment thus shows an eye lens 1 which allows the optical element 10 to be rotated, for example in order to rotate the axial position of a toric lens and thus improve the visual power of the eye by correcting astigmatism.
  • the haptic element 20 also has two optical surfaces (not shown). At least one of the two optical surfaces of the optical element 10 and the haptic element 20 is designed as a third-order freeform surface according to Lohmann or Alvarez.
  • the displacement devices are advantageously designed so that the positional changes made possible (displacement, rotation) between the optical surfaces of the optical element 10 and the haptic element 20 correspond to the directions of movement which are predetermined by the design of the Lohmann or Alvarez surfaces.
  • Such a variant of the exemplary embodiments thus enables a (targeted and reversible) change in the refractive power of the eye lens 1 after an implantation in the eye through the input of energy.
  • optical element 10 for a fifth exemplary embodiment of an eye lens 1 according to the invention for two different refractive values.
  • the optical element 10 is designed as a liquid lens. It comprises four optical surfaces: a front side 12 facing the cornea in the implanted state, a front side inner surface 312, a rear side inner surface 314 and a rear side 14 facing the retina.
  • the optical surfaces are the interfaces of two membranes.
  • a membrane faces the cornea and has the front side 12 and the front side inner surface 312 as boundary surfaces.
  • the further membrane faces the retina and has the rear side 14 and the rear side inner surface 314 as boundary surfaces.
  • the boundary surfaces of the respective membrane are at a distance that decreases with increasing radius from the optical axis A (not shown).
  • a liquid space 300 which can hold liquid 70, is located between the membranes. This is connected to the output channel 40 of compartment 30 and to the input channel 50 of compartment 30.1. A metered delivery of liquid 70 into the liquid space 300 is made possible via an energy input into compartment 30.
  • FIG. 7b shows a larger volume in the liquid space 300 than FIG. 7a.
  • An increase in volume is accompanied by a change in the curvatures of the optical surfaces 12, 312, 314, 14.
  • the radii of curvature in FIG. 7b are smaller than in FIG. 7a.
  • An input of energy into the compartment thus leads to an increase in the refractive power of the optical element 10 of the eye lens 1.
  • the volume in the liquid space 300 can be reduced by introducing energy into compartment 30.1. This leads to larger radii of curvature of the optical surfaces 12, 312, 314, 14 and thus to a reduction in the refractive power of the optical element 10.
  • the exemplary embodiment shown advantageously enables a reversible change in the refractive power of the eye lens 1 and can thus enable an improvement in vision in the implanted state.
  • FIGS. 8a and 8b show side views of an optical element 10 for a sixth embodiment of an eye lens 1 according to the invention for two different refractive powers.
  • the interfaces 12 and 312 as well as 314 and 14 of the membranes each have a constant spacing.
  • the inlet channel 50 of compartment 30 and the outlet channel 40 of compartment 30.1 are each connected to a liquid storage space 320 and 320.1, respectively.
  • it can also be a common liquid storage space.
  • a liquid 70 can be used that is different from aqueous humor and, for example, has a higher refractive index (for visible light) than aqueous humor.
  • This liquid 70 always remains in a closed system, which is here in Example is formed from the liquid storage spaces 320, 320.1, the compartments 30, 30.1 and their inlet and outlet channels as well as the liquid space.
  • FIG. 9 A schematic representation of a correction device 400 is shown in FIG. 9.
  • the energy device configured as a laser device 410 emits a laser beam 415 which is focused via a focusing device 420 in the eye lens 1 implanted in an eye 440.
  • the laser unit 410 is controlled via a control unit 430. From this, signal data are transmitted to the laser unit 410 via a signal data line (shown as an arrow) that is not specified in more detail.
  • the signal data are created on the basis of control data provided by the planning unit P.
  • the planning unit P is part of the correction device 400.
  • the control data are transmitted to the control unit 430 via the interface S, which is part of the planning unit P, via a control line that is not specified in any more detail.
  • the planning unit P can be spatially separated from the correction device 400.
  • the correction device 400 is also designed such that its position in front of the eye 440 can be positioned movably in all three spatial directions (shown in perspective by three double arrows perpendicular to one another).
  • the correction device 400 shown allows on the basis of the
  • Planning device P generated control data to carry out an energy input in the eye lens 1 in the eye 440, which generates a metered delivery of the liquid 70 from the compartment 30, and thus improves the visual performance of the implanted eye.
  • a description of a device relating to method features applies analogously to the corresponding method with regard to these features, while method features correspondingly represent functional features of the device described.

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  • Health & Medical Sciences (AREA)
  • Ophthalmology & Optometry (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Prostheses (AREA)

Abstract

L'invention concerne une lentille oculaire (1) comprenant un élément haptique (20) et un élément optique (10), l'élément optique (10) présentant au moins deux surfaces optiques. L'invention a pour objet de fournir une solution permettant une amélioration de la fonction visuelle après l'implantation de la lentille oculaire (1) sans intervention chirurgicale invasive. La solution selon l'invention porte sur une lentille oculaire (1), comprenant un compartiment (20) qui présente un canal de sortie (40) avec une soupape de sortie (45) et un canal d'entrée (50) avec une soupape d'entrée (55), et qui est conçu pour recevoir un fluide (70). La lentille oculaire (1) permet une entrée d'énergie dans le fluide (70) reçu dans le compartiment (30). Le canal de sortie (40) du compartiment (30) est conçu de telle sorte que, avec l'entrée d'énergie, une décharge dosée du fluide (70) hors du compartiment (30) est générée. La solution selon l'invention porte également sur une unité de planification (P) pour un dispositif de correction (400) ayant un ensemble d'énergie (410), un ensemble de focalisation (420) et une unité de commande (430), qui génère des données de commande, avec lesquelles une entrée d'énergie pour la décharge dosée du fluide (70) est permise. L'invention concerne en outre un dispositif de correction correspondant (400), un procédé de planification et un procédé d'amélioration de la fonction visuelle.
PCT/EP2021/055874 2020-03-11 2021-03-09 Lentille oculaire artificielle WO2021180693A1 (fr)

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US5984962A (en) * 1996-01-22 1999-11-16 Quantum Vision, Inc. Adjustable intraocular lens
US20030060878A1 (en) * 2001-08-31 2003-03-27 Shadduck John H. Intraocular lens system and method for power adjustment
WO2003057022A1 (fr) 2001-12-28 2003-07-17 Calhoun Vision, Inc. Lentilles personnalisees
US6730123B1 (en) * 2000-06-22 2004-05-04 Proteus Vision, Llc Adjustable intraocular lens
US20040169932A1 (en) * 2002-11-20 2004-09-02 Powervision Lens system and methods for power adjustment
DE10105080B4 (de) 2001-02-05 2007-01-18 Marianne Jahn Verstellbare intraokulare Linse und zugehörige Verstellvorrichtung
WO2014077983A1 (fr) 2012-11-14 2014-05-22 Perfect Ip, Llc Système et procédé de modification du caractère hydrophile
US20140200666A1 (en) 2013-01-14 2014-07-17 Andrew F. Phillips Adjustable Toric Intraocular Lens
US10045844B2 (en) * 2002-02-02 2018-08-14 Powervision, Inc. Post-implant accommodating lens modification
US20210100649A1 (en) * 2019-10-04 2021-04-08 Terah Whiting Smiley Adjustable intraocular lenses and methods of post-operatively adjusting intraocular lenses

Patent Citations (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5984962A (en) * 1996-01-22 1999-11-16 Quantum Vision, Inc. Adjustable intraocular lens
US6730123B1 (en) * 2000-06-22 2004-05-04 Proteus Vision, Llc Adjustable intraocular lens
DE10105080B4 (de) 2001-02-05 2007-01-18 Marianne Jahn Verstellbare intraokulare Linse und zugehörige Verstellvorrichtung
US20030060878A1 (en) * 2001-08-31 2003-03-27 Shadduck John H. Intraocular lens system and method for power adjustment
WO2003057022A1 (fr) 2001-12-28 2003-07-17 Calhoun Vision, Inc. Lentilles personnalisees
US10045844B2 (en) * 2002-02-02 2018-08-14 Powervision, Inc. Post-implant accommodating lens modification
US20040169932A1 (en) * 2002-11-20 2004-09-02 Powervision Lens system and methods for power adjustment
WO2014077983A1 (fr) 2012-11-14 2014-05-22 Perfect Ip, Llc Système et procédé de modification du caractère hydrophile
US20140200666A1 (en) 2013-01-14 2014-07-17 Andrew F. Phillips Adjustable Toric Intraocular Lens
US20210100649A1 (en) * 2019-10-04 2021-04-08 Terah Whiting Smiley Adjustable intraocular lenses and methods of post-operatively adjusting intraocular lenses

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