USRE40420E1 - Method and device for treating opaqueness and/or hardening of a closed eye - Google Patents

Method and device for treating opaqueness and/or hardening of a closed eye Download PDF

Info

Publication number
USRE40420E1
USRE40420E1 US11/411,209 US41120900A USRE40420E US RE40420 E1 USRE40420 E1 US RE40420E1 US 41120900 A US41120900 A US 41120900A US RE40420 E USRE40420 E US RE40420E
Authority
US
United States
Prior art keywords
recited
ultrashort pulses
eye
laser
duration
Prior art date
Legal status (The legal status 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 status listed.)
Expired - Lifetime
Application number
US11/411,209
Inventor
Manfred Dick
Eckhard Schroeder
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Carl Zeiss Meditec AG
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
Application granted granted Critical
Publication of USRE40420E1 publication Critical patent/USRE40420E1/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F9/00Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007Methods or devices for eye surgery
    • A61F9/008Methods or devices for eye surgery using laser
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F9/00Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007Methods or devices for eye surgery
    • A61F9/008Methods or devices for eye surgery using laser
    • A61F9/00825Methods or devices for eye surgery using laser for photodisruption
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F9/00Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007Methods or devices for eye surgery
    • A61F9/008Methods or devices for eye surgery using laser
    • A61F9/00825Methods or devices for eye surgery using laser for photodisruption
    • A61F9/00838Correction of presbyopia
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F9/00Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007Methods or devices for eye surgery
    • A61F9/008Methods or devices for eye surgery using laser
    • A61F9/00825Methods or devices for eye surgery using laser for photodisruption
    • A61F9/0084Laser features or special beam parameters therefor
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00017Electrical control of surgical instruments
    • A61B2017/00137Details of operation mode
    • A61B2017/00154Details of operation mode pulsed
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00017Electrical control of surgical instruments
    • A61B2017/00137Details of operation mode
    • A61B2017/00154Details of operation mode pulsed
    • A61B2017/00172Pulse trains, bursts, intermittent continuous operation
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/20Surgical microscopes characterised by non-optical aspects
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F9/00Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007Methods or devices for eye surgery
    • A61F9/008Methods or devices for eye surgery using laser
    • A61F2009/00861Methods or devices for eye surgery using laser adapted for treatment at a particular location
    • A61F2009/0087Lens
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F9/00Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007Methods or devices for eye surgery
    • A61F9/008Methods or devices for eye surgery using laser
    • A61F2009/00861Methods or devices for eye surgery using laser adapted for treatment at a particular location
    • A61F2009/00872Cornea
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F9/00Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007Methods or devices for eye surgery
    • A61F9/008Methods or devices for eye surgery using laser
    • A61F2009/00861Methods or devices for eye surgery using laser adapted for treatment at a particular location
    • A61F2009/00874Vitreous
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F9/00Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007Methods or devices for eye surgery
    • A61F9/008Methods or devices for eye surgery using laser
    • A61F2009/00885Methods or devices for eye surgery using laser for treating a particular disease
    • A61F2009/00887Cataract
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F9/00Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007Methods or devices for eye surgery
    • A61F9/008Methods or devices for eye surgery using laser
    • A61F2009/00885Methods or devices for eye surgery using laser for treating a particular disease
    • A61F2009/00895Presbyopia
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F9/00Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007Methods or devices for eye surgery
    • A61F9/00736Instruments for removal of intra-ocular material or intra-ocular injection, e.g. cataract instruments
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F9/00Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007Methods or devices for eye surgery
    • A61F9/008Methods or devices for eye surgery using laser
    • A61F9/009Auxiliary devices making contact with the eyeball and coupling in laser light, e.g. goniolenses

Definitions

  • the present invention relates to a method and a device for treating opacities and/or hardenings of an unopened eye. Specifically, the present invention relates to a laser system and a method for cleaning, in particular, the ageing human eye from gray hazes in the cornea, the lens or the vitreous body to restore transparency in the eye.
  • opacities develop in the lens (cataract) or in the vitreous body or the cornea.
  • the treatment is presently limited to replacing the lens with a plastic lens during a cataract surgery, replacing the vitreous body with silicone oil by vitrectomy, or also to transplanting the cornea.
  • the laser beam is in both cases led directly to the tissue to be treated.
  • a proven efficient laser is, in particular, the Er:YAG laser having the emission wavelength of 2.94 ⁇ m whose radiation is strongly absorbed by water.
  • cannulas with optical waveguides are led up to the location of treatment.
  • cannulas having diameters of approximately 1 mm are manufacturable now, the necessity of the surgical intervention remains.
  • a device for carrying out a laser phacoemulsification is described, for example, in German Patent 19718139.
  • a further phenomenon which occurs in old age is presbyopia.
  • One reason for this lies in the hardening of the lens, which can occur, for example, due to deposit of substances.
  • PRK photorefractive keratectomy
  • PRK photorefractive keratectomy
  • This objective is achieved, in particular, by a method for dissolving opacities and/or hardenings of an unopened eye in connection with which the opacities and/or hardenings are dissolved via at least one ultrashort pulse of a laser without opening the eye.
  • an ultrashort pulse which is sent through the transparent eye structure, no thermal or athermal damage is produced on the retina or other uninvolved regions.
  • the working plane for example, the lens, the vitreous body or in the cornea
  • there exists an energy density of such a kind that indeed nothing happens in the fully transparent medium of the eye but that disruptions are induced at heterogeneous spots of clouding by local absorption, the disruptions dissolving these impurities. These disruptions result in the evaporation of these impurities.
  • the gas blisters (cavities) possibly forming in the process are filled up in a few hours and disappear in this manner.
  • the dissolved impurities are reduced by resorption and/or dispersion, or disappear completely.
  • Pulses which lie in the ps range are preferably used as ultrashort pulses; particular preference being given to pulses which lie in the fs range. It is preferred to use pulses of from 10 ps to 10 fs, particularly preferably of 300 fs.
  • the special advantage of the method according to the present invention lies in that the opacities and/or hardenings of the eye can be removed or reduced without having to open the eye. In this manner, the risks involved in surgery are avoided.
  • a treatment which is more gentle and carried out in small steps can be accomplished by appropriate selection of the energy of the ultrashort pulse.
  • the ultrashort pulses prefferably be further amplified, particularly preferably via the Chirped Pulse Amplification Method (CPA method).
  • CPA method Chirped Pulse Amplification Method
  • the opacities and/or hardenings are dissolved with the assistance of a pulse train having a duration of less than 5 s, preferably less than 3 s, particularly preferably less than 0.1 s of the ultrashort pulses. It is very particularly preferred to provide pulse lengths in the range of from 10 ps to 10 fs, and especially preferably of approximately 300 fs.
  • the energy input in the region to be treated can be predetermined via the selection of a pulse train by determining the duration. By selecting extremely short pulse trains, it is possible, moreover, to prevent efficiency losses which could occur, for example, because of a movement of the eye during the treatment.
  • the pulses particularly preferably have a duration of less than 10 ps. It is also conceivable to use the pulse train in continuous operation until the desired effect has been attained. Very particularly preferably, it is also possible to use single pulses and very short pulse trains to achieve a particularly gentle treatment by iteratively monitoring the success of treatment.
  • pulse trains with a repetition frequency in particular, with a repetition frequency in the kHz range are emitted.
  • the pulse trains themselves are superposed with a repetition frequency once again.
  • the energy input into the region to be treated can be varied over time once more in spite of the selection of a longer pulse train or even of a continuous operation. Because of this, an even more gentle treatment is possible, avoiding any thermal or athermal damage to the eye in regions which are not intended to be treated.
  • a laser radiation of a wavelength distribution which has a higher absorption and/or a lower reflection for the opacities and/or hardenings than for the remaining parts of the eye.
  • the energy density in such a manner that the density required for triggering an optical breakdown is only reached at locations of local absorption.
  • This selective adjustment is attained through the increased absorption of the opacities and/or hardenings at the selected wavelengths.
  • the wavelength is preferably 350 to 1300 nm. It is particularly preferred to chose a laser to whose radiation the sensitive regions such as the retina or the macula are somewhat less sensitive.
  • ultrashort pulses are aligned in such a manner that energy densities which dissolve the opacities and/or hardenings occur within the opacities and/or hardenings while, at the same time, no damage is caused to the tissue in the sensitive region of the eye.
  • this can be accomplished by a focussing of the beam and a corresponding beam guidance of the pulses.
  • the beam geometry of the pulse it is possible to couple in energy densities in the region of the tissue to be treated which give rise to a disruption (and, consequently, to the dissolution) of the pathological (less transparent) tissue.
  • the beam can be shaped in such a manner that, in the area of sensitive regions such as the retina and, in particular, the macula, energy densities occur which do not result in the destruction of this tissue.
  • the complete eye lens or a region thereof having a preselected size is irradiated with a converging beam of rays and an energy density in the region of the lens below that of the optical breakdown.
  • the focus lies in the vitreous body.
  • the energy is selected such that, given transparency of the lens, an optical breakdown occurs at the focus in the vitreous body. Since all the energy is consumed during the optical breakdown at the focus, it is possible to provide a high level of treatment safety with regard to the macula. Any possible formation of blisters in the vitreous body will relax after a short time.
  • the alignment of the ultrashort pulses takes place via a deflection device and/or focusing optics and/or a contact glass. This makes it possible not only to accurately align the ultrashort pulses and the thereby described beam with the region to be treated but also to preselect the energy density which is desired in the target region. By drawing upon known devices, it is possible for the method according to the present invention to be implemented in cost-effective manner.
  • data on the opacities and/or hardenings is acquired by measuring reflected radiation of low energy prior to the actual treatment, this acquired data being taken into account in the selection of the alignments of the energy of the pulses to be used.
  • this acquired data being taken into account in the selection of the alignments of the energy of the pulses to be used.
  • the energy of the radiation is substantially used up during the disruption of opacities, optimum adaptation of the beam geometry to the opacities to be treated is also advantageous for the gentle treatment of the sensitive regions.
  • the thus acquired data permits individual and well-directed treatment of the identified regions.
  • this data can also be acquired between the individual treatment steps to ascertain the extent of success the treatment has shown so far.
  • blisters are produced in the lens of the eye, and these blisters are filled with liquid without having to open the eye.
  • This formation of blisters inside of the lens gives rise to a loosening of the lens material.
  • the blisters formed in this manner are automatically filled with liquid again. Because of these blisters filled with liquid, a lens is produced which has a higher flexibility than the original lens. However, the accommodation of the lens is thereby increased.
  • the blisters are produced as blister fields in the marginal area of the lens. This placing of blisters in the marginal area or in the marginal zone of the lens results in a softening of the lens upon filling with liquid. This brings about a higher flexibility and, thus, a higher accommodation of the lens. Via a symmetrical arrangement of the blister fields, it is possible for the accommodative capacity of the lens to be preserved symmetrically. In the case that the lens is hardened only partially, then the flexibility of the lens can be increased in a particular region by selective formation of blisters. In this manner, it is possible to improve the overall symmetry of the lens during accommodation.
  • the object of the present invention is achieved, moreover, by a device for treating opacities and/or hardenings of an unopened eye, including a laser having a frequency distribution in the range of from 350 nm to 1300 nm as well as a device for generating ultrashort pulses, provision being made for a device for aligning the ultrashort pulses, including a deflection device and/or focusing optics and/or a contact glass, provision being made for a control device via which the device for aligning the ultrashort pulses is controlled as a function of data on the opacities and/or hardenings.
  • a device for treating opacities and/or hardenings of an unopened eye including a laser having a frequency distribution in the range of from 350 nm to 1300 nm as well as a device for generating ultrashort pulses, provision being made for a device for aligning the ultrashort pulses, including a deflection device and/or focusing optics and/or a
  • the optical means for coupling in the radiation are preferably constituted by tunable focusing optics, deflection mirrors of a micromanipulator, contact glasses, special mirror contact glasses and surgical microscopes or slitlamps.
  • tunable focusing optics deflection mirrors of a micromanipulator
  • contact glasses special mirror contact glasses
  • surgical microscopes or slitlamps it is possible for the beam to be set up and aligned inside of the eye in such a manner that the energy input can be predetermined very precisely in the regions to be treated without the possibility that an energy density might occur outside of these regions to be treated which is detrimental for the tissue existing there.
  • the data which has been ascertained on the regions to be treated can be prepared in such a manner that the pulse duration, sequence, and the energy density to be introduced can be determined and that the device for aligning the ultrashort pulses can be set up and aligned via the control device on the basis of the determined parameters by adjusting the individual elements of the optical system via the control device in such a manner that the desired region can be treated with the predetermined energy input.
  • the laser is selected such that it canlemit pulses in the ps range, preferably in the fs range.
  • the laser as coherent light source includes a device for generating at least one pulse train.
  • This pulse train has preferably a duration of less than 5 s, especially preferably less than 2 s and, particularly preferably, of less than 0.1 s. It is particularly preferred to provide pulse lengths in the range of from 10 ps to 10 fs and, very particularly preferably, pulse lengths of approximately 300 fs.
  • the device according to the present invention is preferably also able to provide pulse trains in continuous operation or to emit single pulses.
  • the device for generating pulse trains with a repetition frequency, particularly preferably in the kHz range, of the laser as coherent light source it is possible to produce the superposition of the individual pulse trains with the repetition frequency described in the method according to the present invention, increasing the gentle introduction of the energy into the region to be treated.
  • the coherent light source particularly preferably features a device for generating a laser radiation having a frequency distribution which has a higher absorption and/or a lower reflection for the opacities and/or hardenings than for the remaining parts of the eye.
  • a tunable laser which is able to radiate in the range of from 350 nm to 1300 nm. It is particularly preferred to provide a laser which is able to radiate in the range of 780 nm, such as a Ti-sapphire laser or, also preferably, in the range of 1060 nm, such as an Nd:glass laser. Using such a laser, it is possible to attain the advantages of the method according to the present invention.
  • the object is achieved according to the present invention by using a device or method according to the present invention for the treatment of haze formation in the cornea subsequent in excimer laser treatments, in the case of cloudings of the lens nucleus, in the case of incipient cataract and/or for impurities of the vitreous body in the visual field.
  • FIG. 1 shows an exemplary embodiment of the device according to the present invention for treating an opacity in the visual field of the vitreous body.
  • FIG. 2 depicts an exemplary embodiment of the present invention for treating presbyopia
  • FIG. 3 depicts a further exemplary embodiment of the present invention for treating the eye lens
  • FIG. 4 shows a further exemplary embodiment of the present invention for treating a particular region of the eye lens
  • FIG. 5 is a diagram of a pulse train with a representation of the time axis and amplitude.
  • FIG. 1 shows a first exemplary embodiment of the present invention for treating an opacity in the vitreous body in the visual field directly behind the lens.
  • Focusing optics 12 are connected downstream of a laser 10 , here a mode-locked laser.
  • a deflection mirror with micromanipulator 14 is arranged downstream of the focusing optics.
  • a contact glass 15 is placed on the eye 1 to be treated.
  • a clouded region 5 is situated downstream of the eye lens.
  • a surgical microscope with slitlamp 19 is used for monitoring.
  • the mode-locked laser system is used to generate ultrashort laser pulses, preferably of 10 ps to 10 fs, which are further amplified using the Chirped Pulse Amplification Method to make available pulse energies above 1 ml in the kHz range.
  • ultrashort laser pulses preferably of 10 ps to 10 fs
  • the transparent regions of the cornea, lens or vitreous body to be treated have a low absorption which are not damaged when irradiated with sufficiently low energy densities of the ultrashort pulse.
  • a focusing device 12 which is used for aligning and focusing the beam is arranged downstream of laser 10 . The beam is focused via deflection mirror with micromanipulator 14 through contact glass 15 onto clouded region 5 .
  • the laser emits pulse trains 25 of ultrashort pulses 20 . These are only absorbed by the pathological clouded regions whereby a selective treatment is rendered possible.
  • the ultrashort pulses result in a locally limited, disruptive size reduction process of the clouded tissue without detrimental thermal side effects.
  • the local, selective and athermal size reduction process restores transparency in this region. Possibly developing cavitations in the vitreous body are refilled with liquid by the body within a short time. In this manner, region 5 becomes transparent again after the treatment.
  • the energy is selected such that the transparent parts of the eye lens do not permit absorption of the selected wavelength.
  • the clouded regions in the eye lens absorb the radiation and thus, the ultrashort pulses give rise to a locally limited, disruptive size reduction process of the clouded tissue also in the eye lens without detrimental thermal side effects.
  • the energy which were not absorbed by the clouded regions are used up by disportion at the focus in the vitreous body and, consequently, cannot damage the retina.
  • the cavitations developing the vitreous body are refilled the liquid of the body within a short time and, consequently, are transparent again.
  • FIG. 2 depicts an exemplary embodiment of the present invention for treating presbyopia.
  • the device corresponds essentially to that in FIG. 1 .
  • the beam deflection of the pulse train takes place via deflection mirror with micromanipulator 14 in such a manner that the focus comes to rest in the marginal area of the lens.
  • the blisters can thus be produced preferably in the marginal area of the lens which, upon filling with preferably endogenous fluid, have a higher flexibility and therefore accommodative capacity. In this manner, it is possible to place whole fields of blisters, resulting in a regional softening of the lens and, consequently, in a corresponding increase in flexibility.
  • FIG. 3 depicts another exemplary embodiment of the present invention for treating the eye lens.
  • This exemplary embodiment also corresponds to that shown in FIG. 1 in its essential design.
  • the beam is widened in such a manner that it can be adjusted in the area of eye lens 2 so as to produce an energy input here which results in a destruction of clouded regions 5 in lens 2 while, in its further course, the beam is widened in such a manner that the energy in the area of macula 7 is so low that no damage can be caused to the tissue here.
  • the radiation is guided during the treatment in such a manner that neither the retina nor any locations other than the pathological ones can be damaged.
  • FIG. 4 is a another exemplary embodiment of the present invention for treating a particular region of eye lens 2 .
  • a mirror 16 is provided in contact glass 15 , the mirror making it possible for the pulse train to be aligned with a particular region of the eye lens.
  • the beam impinges on deflection mirror with micromanipulator 14 which sets up the beam through contact glass 15 onto mirror 16 in contact glass 15 , the mirror 16 aligning the beam with the area of eye lens 2 in which clouded region 5 exist.
  • FIG. 5 shows a diagram of a pulse train 25 with a representation of the time axis and amplitude.
  • the individual ultrashort pulses 20 have a width of several femto-seconds.
  • Pulse train 25 is formed of three pulse bursts 22 of different lengths 22.1, 22.2 and 22.3, and superposed with a frequency sequence having the period T. In this manner, the energy input via the ultrashort pulses can be further varied. While time t is represented on the x-axis, amplitude A is indicated on the y-axis. In lieu of a frequency sequence in the kHz range, a linear or a quasi-linear rising envelope or falling envelope can also be thought of.
  • First pulse burst 22.1 is constituted by one single pulse 20 .
  • Pulse train 22.2 is constituted by several single pulses which, in turn, are spaced from one another by time T. T usually lies in the ms range while the width of single pulses 20 lies in the fs range. Pulse train 25 is formed of the pulse bursts together with pulse burst 22.3.
  • a method at and a device for treating opacities and/or hardenings of an unopened eye was introduced.
  • a special advantage of the design approach according to the present invention is that it enables treatments to be carried out inside the eye without having to introduce a surgical instrument into the eye.

Abstract

The present invention relates to a method and a device for treating opacities and/or hardenings of an unopened eye.
It is a specific advantage of the solution according to the invention that the treamtment of the inner region of the eye is possible without the need to introduce a surgical instrument into the eye.

Description

BACKGROUND OF THE INVENTION
The present invention relates to a method and a device for treating opacities and/or hardenings of an unopened eye. Specifically, the present invention relates to a laser system and a method for cleaning, in particular, the ageing human eye from gray hazes in the cornea, the lens or the vitreous body to restore transparency in the eye.
In ophthalmology, it is known that, in particular in the ageing eye, opacities develop in the lens (cataract) or in the vitreous body or the cornea. At the advanced stage, the treatment is presently limited to replacing the lens with a plastic lens during a cataract surgery, replacing the vitreous body with silicone oil by vitrectomy, or also to transplanting the cornea. It is known to carry out the surgery of the cataract and the vitrectomy of the vitreous body using a laser. During a surgery, the laser beam is in both cases led directly to the tissue to be treated. A proven efficient laser is, in particular, the Er:YAG laser having the emission wavelength of 2.94 μm whose radiation is strongly absorbed by water. For conveying the laser radiation, cannulas with optical waveguides are led up to the location of treatment. Although cannulas having diameters of approximately 1 mm are manufacturable now, the necessity of the surgical intervention remains. A device for carrying out a laser phacoemulsification is described, for example, in German Patent 19718139.
Also known are surgical techniques in the case of which the eye is not opened but the laser light is guided into the eye via the normal path of the visual process. These techniques include the possibility of attaining an optical disruption inside of the cornea by focusing fs laser pulses (300 fs, 1 μl, 780 nm), resulting in the formation of blisters. By folding open a lamella, it is possible to prepare an intrastromal lenticle whose removal brings about a refractive correction. It is known, moreover, that the gray after-cataract membrane can be disruptively removed with the aid of ns pulses of a Q-switched Nd:YAG laser.
In known methods heretofore, apart from medicamentous methods, it was not possible to treat the clouded regions already at the initial stage. Thus, the known laser techniques are not suitable for removing the clouded regions in the eye without opening the eye. Therefore, it is an object of the present invention to provide a method and a device which make it possible to dissolve clouded regions in the eye.
A further phenomenon which occurs in old age is presbyopia. One reason for this lies in the hardening of the lens, which can occur, for example, due to deposit of substances. Apart from the utilization of spectacles, photorefractive keratectomy (PRK) has often been used recently for correcting the visual defect. Removal of the hardening itself has not been possible in known methods heretofore. Therefore, it is a further object of the present invention to provide a device with which the lens' ability to contract is increased again.
SUMMARY OF THE INVENTION
Therefore, it is an object of the present invention to provide a method and a device which make it possible to dissolve opacities and/or hardenings of an eye.
This objective is achieved, in particular, by a method for dissolving opacities and/or hardenings of an unopened eye in connection with which the opacities and/or hardenings are dissolved via at least one ultrashort pulse of a laser without opening the eye. By using an ultrashort pulse which is sent through the transparent eye structure, no thermal or athermal damage is produced on the retina or other uninvolved regions. In the working plane (for example, the lens, the vitreous body or in the cornea), there exists an energy density of such a kind that indeed nothing happens in the fully transparent medium of the eye but that disruptions are induced at heterogeneous spots of clouding by local absorption, the disruptions dissolving these impurities. These disruptions result in the evaporation of these impurities.
The gas blisters (cavities) possibly forming in the process are filled up in a few hours and disappear in this manner. The dissolved impurities are reduced by resorption and/or dispersion, or disappear completely.
Pulses which lie in the ps range are preferably used as ultrashort pulses; particular preference being given to pulses which lie in the fs range. It is preferred to use pulses of from 10 ps to 10 fs, particularly preferably of 300 fs.
The special advantage of the method according to the present invention lies in that the opacities and/or hardenings of the eye can be removed or reduced without having to open the eye. In this manner, the risks involved in surgery are avoided. Using the method according to the present invention, moreover, a treatment which is more gentle and carried out in small steps can be accomplished by appropriate selection of the energy of the ultrashort pulse.
It is preferred for the ultrashort pulses to be further amplified, particularly preferably via the Chirped Pulse Amplification Method (CPA method).
In a preferred method according to the present invention, the opacities and/or hardenings are dissolved with the assistance of a pulse train having a duration of less than 5 s, preferably less than 3 s, particularly preferably less than 0.1 s of the ultrashort pulses. It is very particularly preferred to provide pulse lengths in the range of from 10 ps to 10 fs, and especially preferably of approximately 300 fs. The energy input in the region to be treated can be predetermined via the selection of a pulse train by determining the duration. By selecting extremely short pulse trains, it is possible, moreover, to prevent efficiency losses which could occur, for example, because of a movement of the eye during the treatment. The pulses particularly preferably have a duration of less than 10 ps. It is also conceivable to use the pulse train in continuous operation until the desired effect has been attained. Very particularly preferably, it is also possible to use single pulses and very short pulse trains to achieve a particularly gentle treatment by iteratively monitoring the success of treatment.
In a further preferred method of the present invention, pulse trains with a repetition frequency, in particular, with a repetition frequency in the kHz range are emitted. In this connection, the pulse trains themselves are superposed with a repetition frequency once again. In this manner, the energy input into the region to be treated can be varied over time once more in spite of the selection of a longer pulse train or even of a continuous operation. Because of this, an even more gentle treatment is possible, avoiding any thermal or athermal damage to the eye in regions which are not intended to be treated.
In a further preferred method of the present invention, one chooses a laser radiation of a wavelength distribution which has a higher absorption and/or a lower reflection for the opacities and/or hardenings than for the remaining parts of the eye. In this manner, it is possible to adjust the energy density in such a manner that the density required for triggering an optical breakdown is only reached at locations of local absorption. This selective adjustment is attained through the increased absorption of the opacities and/or hardenings at the selected wavelengths. It is particularly preferred to chose a laser for whose wavelength the eye is highly transmissive. The wavelength is preferably 350 to 1300 nm. It is particularly preferred to chose a laser to whose radiation the sensitive regions such as the retina or the macula are somewhat less sensitive. This can be accomplished via a lower absorptivity of these regions in the eye for the selected radiation. This can also be achieved by a higher reflectivity of the regions of the eye which are not to be treated. Thus, the radiation cannot cause any damage in the regions of the eye which are not to be treated just because of the absorptive and reflective behavior, independently of the energy density which can be generated by focusing.
In a further preferred method of the present invention, ultrashort pulses are aligned in such a manner that energy densities which dissolve the opacities and/or hardenings occur within the opacities and/or hardenings while, at the same time, no damage is caused to the tissue in the sensitive region of the eye. Apart from the selection of the wavelength, this can be accomplished by a focussing of the beam and a corresponding beam guidance of the pulses. Thus, by shaping the beam geometry of the pulse, it is possible to couple in energy densities in the region of the tissue to be treated which give rise to a disruption (and, consequently, to the dissolution) of the pathological (less transparent) tissue. At the same time, the beam can be shaped in such a manner that, in the area of sensitive regions such as the retina and, in particular, the macula, energy densities occur which do not result in the destruction of this tissue.
This can preferably be attained via the beam guidance in that, upon passage of the beam through the target region to be treated, the beam is widened in such a manner that the energy densities in the sensitive region are so low that the region cannot be damaged. In a further preferred method, the complete eye lens or a region thereof having a preselected size is irradiated with a converging beam of rays and an energy density in the region of the lens below that of the optical breakdown. In the process, the focus lies in the vitreous body. On the other hand, the energy is selected such that, given transparency of the lens, an optical breakdown occurs at the focus in the vitreous body. Since all the energy is consumed during the optical breakdown at the focus, it is possible to provide a high level of treatment safety with regard to the macula. Any possible formation of blisters in the vitreous body will relax after a short time.
In a further preferred method of the present invention, the alignment of the ultrashort pulses takes place via a deflection device and/or focusing optics and/or a contact glass. This makes it possible not only to accurately align the ultrashort pulses and the thereby described beam with the region to be treated but also to preselect the energy density which is desired in the target region. By drawing upon known devices, it is possible for the method according to the present invention to be implemented in cost-effective manner.
In another preferred method of the present invention, data on the opacities and/or hardenings is acquired by measuring reflected radiation of low energy prior to the actual treatment, this acquired data being taken into account in the selection of the alignments of the energy of the pulses to be used. To protect the sensitive regions, in fact, it lies especially also within the scope of the present invention to irradiate with considerably lower intensities which are harmless to the eye prior to the actual therapeutic radiation, and to draw conclusions on the alignment of the laser and on the radiation dose required in the specific radiation direction on the basis of the radiation which is reflected, for example, at the opacities. Since the energy of the radiation is substantially used up during the disruption of opacities, optimum adaptation of the beam geometry to the opacities to be treated is also advantageous for the gentle treatment of the sensitive regions. The thus acquired data permits individual and well-directed treatment of the identified regions. In particular, this data can also be acquired between the individual treatment steps to ascertain the extent of success the treatment has shown so far. Thus, it is possible, for example, to sent a low-energy signal after an ultrashort pulse or a pulse train to obtain data therefrom on the changes caused by the ultrashort pulse or pulse train in the region to be treated.
In a further method according to the present invention for treating the presbyopia of an eye, blisters are produced in the lens of the eye, and these blisters are filled with liquid without having to open the eye. This formation of blisters inside of the lens gives rise to a loosening of the lens material. The blisters formed in this manner are automatically filled with liquid again. Because of these blisters filled with liquid, a lens is produced which has a higher flexibility than the original lens. However, the accommodation of the lens is thereby increased.
It is particularly preferred for the blisters to be produced as blister fields in the marginal area of the lens. This placing of blisters in the marginal area or in the marginal zone of the lens results in a softening of the lens upon filling with liquid. This brings about a higher flexibility and, thus, a higher accommodation of the lens. Via a symmetrical arrangement of the blister fields, it is possible for the accommodative capacity of the lens to be preserved symmetrically. In the case that the lens is hardened only partially, then the flexibility of the lens can be increased in a particular region by selective formation of blisters. In this manner, it is possible to improve the overall symmetry of the lens during accommodation.
The object of the present invention is achieved, moreover, by a device for treating opacities and/or hardenings of an unopened eye, including a laser having a frequency distribution in the range of from 350 nm to 1300 nm as well as a device for generating ultrashort pulses, provision being made for a device for aligning the ultrashort pulses, including a deflection device and/or focusing optics and/or a contact glass, provision being made for a control device via which the device for aligning the ultrashort pulses is controlled as a function of data on the opacities and/or hardenings. Using this device, it is possible to accomplish the above advantages of the method according to the present invention. The optical means for coupling in the radiation are preferably constituted by tunable focusing optics, deflection mirrors of a micromanipulator, contact glasses, special mirror contact glasses and surgical microscopes or slitlamps. Using these elements, it is possible for the beam to be set up and aligned inside of the eye in such a manner that the energy input can be predetermined very precisely in the regions to be treated without the possibility that an energy density might occur outside of these regions to be treated which is detrimental for the tissue existing there. In a further preferred exemplary embodiment of the present invention, provision is made for a control device via which the device for aligning the ultrashort pulses can be controlled, particularly preferably as a function of data on the opacities and/or hardenings. Using this control device, the data which has been ascertained on the regions to be treated can be prepared in such a manner that the pulse duration, sequence, and the energy density to be introduced can be determined and that the device for aligning the ultrashort pulses can be set up and aligned via the control device on the basis of the determined parameters by adjusting the individual elements of the optical system via the control device in such a manner that the desired region can be treated with the predetermined energy input. The laser is selected such that it canlemit pulses in the ps range, preferably in the fs range.
In a further refinement, the laser as coherent light source includes a device for generating at least one pulse train. This pulse train has preferably a duration of less than 5 s, especially preferably less than 2 s and, particularly preferably, of less than 0.1 s. It is particularly preferred to provide pulse lengths in the range of from 10 ps to 10 fs and, very particularly preferably, pulse lengths of approximately 300 fs. The device according to the present invention is preferably also able to provide pulse trains in continuous operation or to emit single pulses. Using the device for generating pulse trains with a repetition frequency, particularly preferably in the kHz range, of the laser as coherent light source, it is possible to produce the superposition of the individual pulse trains with the repetition frequency described in the method according to the present invention, increasing the gentle introduction of the energy into the region to be treated.
The coherent light source particularly preferably features a device for generating a laser radiation having a frequency distribution which has a higher absorption and/or a lower reflection for the opacities and/or hardenings than for the remaining parts of the eye. For that purpose, it is particularly preferred to use a tunable laser which is able to radiate in the range of from 350 nm to 1300 nm. It is particularly preferred to provide a laser which is able to radiate in the range of 780 nm, such as a Ti-sapphire laser or, also preferably, in the range of 1060 nm, such as an Nd:glass laser. Using such a laser, it is possible to attain the advantages of the method according to the present invention.
The object is achieved according to the present invention by using a device or method according to the present invention for the treatment of haze formation in the cornea subsequent in excimer laser treatments, in the case of cloudings of the lens nucleus, in the case of incipient cataract and/or for impurities of the vitreous body in the visual field.
BRIEF DESCRIPTION OF THE DRAWINGS
In the following, exemplary embodiments of the present invention and advantageous refinements will be explained in greater detail on the basis of drawings. In this context,
FIG. 1 shows an exemplary embodiment of the device according to the present invention for treating an opacity in the visual field of the vitreous body.
FIG. 2 depicts an exemplary embodiment of the present invention for treating presbyopia;
FIG. 3 depicts a further exemplary embodiment of the present invention for treating the eye lens;
FIG. 4 shows a further exemplary embodiment of the present invention for treating a particular region of the eye lens; and
FIG. 5 is a diagram of a pulse train with a representation of the time axis and amplitude.
DETAILED DESCRIPTION
FIG. 1 shows a first exemplary embodiment of the present invention for treating an opacity in the vitreous body in the visual field directly behind the lens. Focusing optics 12 are connected downstream of a laser 10, here a mode-locked laser. A deflection mirror with micromanipulator 14 is arranged downstream of the focusing optics. A contact glass 15 is placed on the eye 1 to be treated. A clouded region 5 is situated downstream of the eye lens. A surgical microscope with slitlamp 19 is used for monitoring.
The mode-locked laser system is used to generate ultrashort laser pulses, preferably of 10 ps to 10 fs, which are further amplified using the Chirped Pulse Amplification Method to make available pulse energies above 1 ml in the kHz range. At the wavelength of 780 nm (Ti-sapphire) or 1060 nm (Nd:glass), the transparent regions of the cornea, lens or vitreous body to be treated have a low absorption which are not damaged when irradiated with sufficiently low energy densities of the ultrashort pulse. A focusing device 12 which is used for aligning and focusing the beam is arranged downstream of laser 10. The beam is focused via deflection mirror with micromanipulator 14 through contact glass 15 onto clouded region 5.
During operation, the laser emits pulse trains 25 of ultrashort pulses 20. These are only absorbed by the pathological clouded regions whereby a selective treatment is rendered possible. In the process, the ultrashort pulses result in a locally limited, disruptive size reduction process of the clouded tissue without detrimental thermal side effects. Upon the filling of the induced blisters, the local, selective and athermal size reduction process restores transparency in this region. Possibly developing cavitations in the vitreous body are refilled with liquid by the body within a short time. In this manner, region 5 becomes transparent again after the treatment.
Given an appropriate selection of energy, it is also possible to treat clouded regions in the eye lens using this arrangement. In this connection, the energy is selected such that the transparent parts of the eye lens do not permit absorption of the selected wavelength. The clouded regions in the eye lens, however, absorb the radiation and thus, the ultrashort pulses give rise to a locally limited, disruptive size reduction process of the clouded tissue also in the eye lens without detrimental thermal side effects. The energy which were not absorbed by the clouded regions are used up by disportion at the focus in the vitreous body and, consequently, cannot damage the retina. The cavitations developing the vitreous body are refilled the liquid of the body within a short time and, consequently, are transparent again.
FIG. 2 depicts an exemplary embodiment of the present invention for treating presbyopia. The device corresponds essentially to that in FIG. 1. However, the beam deflection of the pulse train takes place via deflection mirror with micromanipulator 14 in such a manner that the focus comes to rest in the marginal area of the lens. According to the present invention, the blisters can thus be produced preferably in the marginal area of the lens which, upon filling with preferably endogenous fluid, have a higher flexibility and therefore accommodative capacity. In this manner, it is possible to place whole fields of blisters, resulting in a regional softening of the lens and, consequently, in a corresponding increase in flexibility.
FIG. 3 depicts another exemplary embodiment of the present invention for treating the eye lens. This exemplary embodiment also corresponds to that shown in FIG. 1 in its essential design. Via optical system 12 used here, however, the beam is widened in such a manner that it can be adjusted in the area of eye lens 2 so as to produce an energy input here which results in a destruction of clouded regions 5 in lens 2 while, in its further course, the beam is widened in such a manner that the energy in the area of macula 7 is so low that no damage can be caused to the tissue here.
Via special divergent beam guidance and appropriate irradiation as well as possible automated scanning methods, the radiation is guided during the treatment in such a manner that neither the retina nor any locations other than the pathological ones can be damaged.
FIG. 4 is a another exemplary embodiment of the present invention for treating a particular region of eye lens 2. In this context, a mirror 16 is provided in contact glass 15, the mirror making it possible for the pulse train to be aligned with a particular region of the eye lens. The beam impinges on deflection mirror with micromanipulator 14 which sets up the beam through contact glass 15 onto mirror 16 in contact glass 15, the mirror 16 aligning the beam with the area of eye lens 2 in which clouded region 5 exist.
FIG. 5 shows a diagram of a pulse train 25 with a representation of the time axis and amplitude. The individual ultrashort pulses 20 have a width of several femto-seconds. Pulse train 25 is formed of three pulse bursts 22 of different lengths 22.1, 22.2 and 22.3, and superposed with a frequency sequence having the period T. In this manner, the energy input via the ultrashort pulses can be further varied. While time t is represented on the x-axis, amplitude A is indicated on the y-axis. In lieu of a frequency sequence in the kHz range, a linear or a quasi-linear rising envelope or falling envelope can also be thought of. First pulse burst 22.1 is constituted by one single pulse 20. Pulse train 22.2 is constituted by several single pulses which, in turn, are spaced from one another by time T. T usually lies in the ms range while the width of single pulses 20 lies in the fs range. Pulse train 25 is formed of the pulse bursts together with pulse burst 22.3.
According to the present invention, a method at and a device for treating opacities and/or hardenings of an unopened eye was introduced. A special advantage of the design approach according to the present invention is that it enables treatments to be carried out inside the eye without having to introduce a surgical instrument into the eye.
List of Reference Symbols
  • 1. eye
  • 2. lens
  • 3. vitreous body
  • 4. cornea
  • 5. opacities
  • 7. macula
  • 10. laser
  • 12. optical system (focusing optics)
  • 14. deflection mirror with micromanipulator
  • 15. contact glass
  • 16. mirror in the contact glass
  • 19. surgical microscope with slitlamp
  • 20. ultrashort pulse
  • 22. pulse burst
  • 25. pulse train

Claims (43)

1. A method for noninvasively dissolving opacities and/or hardenings of an eye comprising:
dissolvingdirecting a plurality of ultrashort pulses of a laser on an opacity and/or hardening of the eye so as to dissolve at least one of anthe opacity and athe hardening via a, wherein the ultrashort pulses have a duration of less than 10 ps and the plurality of ultrashort pulses of a laser definingdefine a pulse train having a duration of less than 1 s.
2. The method as recited in claim 1, wherein the duration of the pulse train is less than 0.1 s.
3. The method as recited in claim 1, wherein the pulse train is emitted repeatedly.
4. The method as recited in claim 3, wherein a repetition frequency of the pulses in the repeated pulse train is in the kHz range.
5. The method as recited in claim 1, further comprising
selecting a laser radiation of a wavelength which has at least one of a higher absorption and a lower reflection for the at least one of the opacity and the hardening than for a remaining part of the eye.
6. The method as recited in claim 1, further comprising aligning the ultrashort pulses so that energy densities which dissolve the at least one of the opacities and hardenings occur within the at least one of the opacity and the hardening while, at the same time, no damage is caused to tissue in other regions of the eye.
7. The method as recited in claim 6, wherein the alignment of the ultrashort pulses takes place via at least one of a deflection device, focusing optics and a contact glass.
8. The method as recited in claim 1, further comprising
acquiring data on the at least one of the opacity and the hardening by measuring reflected radiation of low energy prior to actual treatment, and
selecting the alignment and the energy of the ultrashort pulses as a function of the acquired data.
9. A method for operating a device according to claim 1 14, the method comprising:
using the device subsequent to an excimer laser treatment in the case of haze formation in the cornea.
10. The method for operating a device according to claim 1 14, the method comprising using the device to treat cloudings of a lens nucleus in the case of incipient cataract.
11. The method for operating a device according to claim 1, the method comprising using the device to treat impurties impurities in a vitreous body in a visual field.
12. A method for noninvasively treating the presbyopia of an eye comprising
using the method of claim 1, and producing blisters in a lens of the eye, the blisters filling with liquid.
13. The method as recited in claim 12, wherein the blisters are produced as blister fields in the lens.
14. A device for noninvasively treating opacities and/or hardenings of an eye comprising:
a laser having a wavelength in a range of from 350 nm to 1300 nm; and
a device for generating a pulse train of ultrashort pulses having a pulse duration of less than 10 ps from the laser, the pulse train having a duration of less than 1 s,
an aligning device for aligning the ultrashort pulses, the aligning device including one of a deflection device, focusing optics, and a contact glass, and
a control device controlling the aligning device for aligning the ultrashort pulses as a function of data on at least one of the opacity and the hardening.
15. The device as recited in claim 14, wherein the duration of the pulse train is less than 0.1 s.
16. The device as recited in claim 14, wherein the device for generating a pulse train generates pulse trains with a repetition frequency.
17. The device as recited in claim 16, wherein the device for generating pulse trains with a repetition frequency generates pulse trains in the kHz range.
18. The device as recited in claim 14, further comprising a device for generating a laser radiation having a wavelength which has at least one of a higher absorption and a lower reflection for the at least one of the opacity and the hardening than for remaining parts of the eye.
19. The device as recited in claim 14, wherein the wavelength of the laser is in the range of from 780 nm to 1060 nm.
20. A method for noninvasively dissolving opacities and/or hardenings of an eye comprising:
dissolvingdirecting a plurality of ultrashort pulses of a laser on an opacity and/or hardening of the eye so as to dissolve at least one of anthe opacity and athe hardening via a, wherein the plurality of ultrashort pulses of a laser defininghave a duration of less than 10 ps and a pulse train, wherein the pulse train is emitted repeatedly and wherein a repetition frequency of the pulses in the repeated pulse train is in the kHz range.
21. The method as recited in claim 20 wherein the method is used for treating a haze formation subsequent to an excimer laser treatment.
22. The method as recited in claim 20 wherein the method is used for treating cloudings of a lens nucleus in the case of an incipient cataract.
23. The method as recited in claim 20 wherein the method is used for treating impurities in a vitreous body in a visual field.
24. A method for noninvasively treating the presbyopia of an eye comprising:
dissolvingdirecting a plurality of ultrashort pulses of a laser on an opacity and/or hardening of the eye so as to dissolve at least one of anthe opacity and athe hardening via a, wherein the plurality of ultrashort pulses of a laser defininghave a duration of less than 10 ps and define a pulse train, and wherein the directing is performed so as to produce blisters as blister fields in a lens of the eye, the blisters filling with liquid.
25. The method as recited in claim 24, wherein the blister fields are produced inside of the lens.
26. The method as recited in claim 25, wherein the blister fields are symmetrically arranged.
27. A method for noninvasively treating the presbyopia of an eye comprising: directing a plurality of ultrashort pulses of a laser on an opacity and/or hardening of the eye so as to dissolve at least one of the opacity and the hardening, wherein the plurality of ultrashort pulses have a duration of less than 10 ps and define a pulse train, and wherein the directing is performed so as to produce blisters in a lens of the eye, and results in an increasing flexibility of the lens.
28. The method as recited in claim 27, wherein the directing is performed so as to produce the blisters inside of the lens.
29. The method as recited in claim 28, wherein the directing is performed so as to produce the blisters in a symmetrically arrangement.
30. The method as recited in claim 27 wherein the ultrashort pulses have a duration in the fs range.
31. A method for noninvasively treating the presbyopia of an eye comprising: directing a plurality of ultrashort pulses of a laser having a duration of less than 10 ps to an inside of a lens of the eye so as to dissolve at least one of an opacity and a hardening in the lens, wherein the directing results in an increased flexibility of the lens.
32. The method as recited in claim 31, wherein the ultrashort pulses have a duration in the fs range.
33. The method as recited in claim 31, wherein the ultrashort pulses have a duration in the ps range.
34. The method as recited in claim 31, wherein the ultrashort pulses have a duration from 10 ps to 10 fs.
35. The method as recited in claim 31, further comprising amplifying the ultrashort pulses.
36. The method as recited in claim 35, wherein the amplification is performed using the Chirped Pulse Amplification Method.
37. The method as recited in claim 31, wherein the directing of the ultrashort pulses includes aligning the ultrashort pulses using at least one of a deflection device, focusing optics and a contact glass.
38. The method as recited in claim 37, wherein the aligning, of the ultrashort pulses includes preselecting an energy, density of the ultrashort pulses at the inside of the lens.
39. A device for noninvasively treating the presbyopia of an eye comprising: a laser configured to emit ultrashort pulses having a pulse duration in the fs range in a pulse train having a duration of less than 5 seconds; an aligning device for aligning the ultrashort pulses, the aligning device including one of a deflection device, focusing optics, and a contact glass; and a control device controlling the aligning device for aligning the ultrashort pulses such that a focus of the ultrashort pulses comes to rest in an inside of the lens.
40. The device as recited in claim 39, wherein the laser is configured to emit the ultrashort pulses in a pulse train having a duration of less than 2 seconds.
41. The device as recited in claim 40, wherein the laser is configured to emit the ultrashort pulses in a pulse train having a duration of less than 0.1 seconds.
42. The method as recited in claim 41, wherein the ultrashort pulses have a duration of approximately 300 fs.
43. The method as recited in claim 1, wherein the ultrashort pulses have a duration of from 10 ps to 10 fs.
US11/411,209 1999-08-26 2000-08-25 Method and device for treating opaqueness and/or hardening of a closed eye Expired - Lifetime USRE40420E1 (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE19940712A DE19940712A1 (en) 1999-08-26 1999-08-26 Method and device for treating opacities and / or hardening of an unopened eye
PCT/EP2000/008308 WO2001013838A1 (en) 1999-08-26 2000-08-25 Method and device for treating opaqueness and/or hardening of a closed eye

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US10/069,607 Reissue US6726679B1 (en) 1999-08-26 2000-08-25 Method and device for treating opaqueness and/or hardening of a closed eye

Publications (1)

Publication Number Publication Date
USRE40420E1 true USRE40420E1 (en) 2008-07-01

Family

ID=7919824

Family Applications (2)

Application Number Title Priority Date Filing Date
US10/069,607 Ceased US6726679B1 (en) 1999-08-26 2000-08-25 Method and device for treating opaqueness and/or hardening of a closed eye
US11/411,209 Expired - Lifetime USRE40420E1 (en) 1999-08-26 2000-08-25 Method and device for treating opaqueness and/or hardening of a closed eye

Family Applications Before (1)

Application Number Title Priority Date Filing Date
US10/069,607 Ceased US6726679B1 (en) 1999-08-26 2000-08-25 Method and device for treating opaqueness and/or hardening of a closed eye

Country Status (6)

Country Link
US (2) US6726679B1 (en)
EP (2) EP1537841B1 (en)
AT (1) ATE290357T1 (en)
AU (1) AU6703400A (en)
DE (2) DE19940712A1 (en)
WO (1) WO2001013838A1 (en)

Cited By (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070185475A1 (en) * 2006-01-20 2007-08-09 Frey Rudolph W System and method for providing the shaped structural weakening of the human lens with a laser
US7655002B2 (en) * 1996-03-21 2010-02-02 Second Sight Laser Technologies, Inc. Lenticular refractive surgery of presbyopia, other refractive errors, and cataract retardation
US8382745B2 (en) 2009-07-24 2013-02-26 Lensar, Inc. Laser system and method for astigmatic corrections in association with cataract treatment
US8465478B2 (en) 2009-07-24 2013-06-18 Lensar, Inc. System and method for performing LADAR assisted procedures on the lens of an eye
US8480659B2 (en) 2008-07-25 2013-07-09 Lensar, Inc. Method and system for removal and replacement of lens material from the lens of an eye
US8500723B2 (en) 2008-07-25 2013-08-06 Lensar, Inc. Liquid filled index matching device for ophthalmic laser procedures
US8556425B2 (en) 2010-02-01 2013-10-15 Lensar, Inc. Purkinjie image-based alignment of suction ring in ophthalmic applications
USD694890S1 (en) 2010-10-15 2013-12-03 Lensar, Inc. Laser system for treatment of the eye
USD695408S1 (en) 2010-10-15 2013-12-10 Lensar, Inc. Laser system for treatment of the eye
US8617146B2 (en) 2009-07-24 2013-12-31 Lensar, Inc. Laser system and method for correction of induced astigmatism
US8758332B2 (en) 2009-07-24 2014-06-24 Lensar, Inc. Laser system and method for performing and sealing corneal incisions in the eye
US8801186B2 (en) 2010-10-15 2014-08-12 Lensar, Inc. System and method of scan controlled illumination of structures within an eye
US8807752B2 (en) 2012-03-08 2014-08-19 Technolas Perfect Vision Gmbh System and method with refractive corrections for controlled placement of a laser beam's focal point
US9180051B2 (en) 2006-01-20 2015-11-10 Lensar Inc. System and apparatus for treating the lens of an eye
US9375349B2 (en) 2006-01-20 2016-06-28 Lensar, Llc System and method for providing laser shot patterns to the lens of an eye
US9393154B2 (en) 2011-10-28 2016-07-19 Raymond I Myers Laser methods for creating an antioxidant sink in the crystalline lens for the maintenance of eye health and physiology and slowing presbyopia development
US9545338B2 (en) 2006-01-20 2017-01-17 Lensar, Llc. System and method for improving the accommodative amplitude and increasing the refractive power of the human lens with a laser
US9889043B2 (en) 2006-01-20 2018-02-13 Lensar, Inc. System and apparatus for delivering a laser beam to the lens of an eye
US10463541B2 (en) 2011-03-25 2019-11-05 Lensar, Inc. System and method for correcting astigmatism using multiple paired arcuate laser generated corneal incisions
US10716706B2 (en) 2011-04-07 2020-07-21 Bausch & Lomb Incorporated System and method for performing lens fragmentation

Families Citing this family (53)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7169123B2 (en) 1997-01-22 2007-01-30 Advanced Medical Optics, Inc. Control of pulse duty cycle based upon footswitch displacement
US6780165B2 (en) 1997-01-22 2004-08-24 Advanced Medical Optics Micro-burst ultrasonic power delivery
DE10162166A1 (en) * 2001-12-12 2003-06-18 Friedrich Schiller Uni Jena Bu Process for removing waste products that result from laser-induced plasma formation during material removal in transparent objects
US7077820B1 (en) 2002-10-21 2006-07-18 Advanced Medical Optics, Inc. Enhanced microburst ultrasonic power delivery system and method
US7316664B2 (en) 2002-10-21 2008-01-08 Advanced Medical Optics, Inc. Modulated pulsed ultrasonic power delivery system and method
CA2830583C (en) 2003-03-12 2015-06-09 Abbott Medical Optics Inc. System and method for pulsed ultrasonic power delivery employing cavitation effects
US7351241B2 (en) * 2003-06-02 2008-04-01 Carl Zeiss Meditec Ag Method and apparatus for precision working of material
US7846126B2 (en) 2003-07-14 2010-12-07 Abbott Medical Optics, Inc. System and method for modulated surgical procedure irrigation and aspiration
DE10358927B4 (en) 2003-12-16 2021-09-09 Carl Zeiss Meditec Ag Laser device and method for material processing by means of laser radiation
US8186357B2 (en) * 2004-01-23 2012-05-29 Rowiak Gmbh Control device for a surgical laser
JP5060949B2 (en) 2004-06-28 2012-10-31 トプコン・メディカル・レーザー・システムズ・インコーポレイテッド Optical scanning system for performing therapy
US9072589B2 (en) 2005-11-17 2015-07-07 Wavelight Gmbh Assembly and method for performing surgical laser treatments of the eye
ES2374819T3 (en) * 2005-11-17 2012-02-22 Wavelight Gmbh PROVISION TO PERFORM SURGICAL TREATMENTS WITH LASER EYE.
EP1792592B1 (en) 2005-12-01 2011-09-14 WaveLight GmbH Arrangement for carrying out surgical laser treatments of the eye
US9681985B2 (en) * 2005-12-01 2017-06-20 Topcon Medical Laser Systems, Inc. System and method for minimally traumatic ophthalmic photomedicine
ES2407996T3 (en) * 2006-04-11 2013-06-17 Wavelight Gmbh Laser device for ophthalmic surgery
US7785336B2 (en) 2006-08-01 2010-08-31 Abbott Medical Optics Inc. Vacuum sense control for phaco pulse shaping
EP1897520B1 (en) * 2006-09-07 2010-11-10 Ziemer Holding AG Ophthalmological device for the refractive correction of an eye.
EP2094208B1 (en) 2006-11-10 2013-09-04 Lars Michael Larsen Apparatus for non or minimally disruptive photomanipulation of an eye
EP2649971B1 (en) 2007-03-13 2016-08-31 Optimedica Corporation Apparatus for creating ocular surgical and relaxing incisions
US8568393B2 (en) * 2007-03-13 2013-10-29 Topcon Medical Laser Systems, Inc. Computer guided patterned laser trabeculoplasty
JP5623907B2 (en) * 2007-09-05 2014-11-12 アルコン レンゼックス, インコーポレーテッド Laser-induced protective shield in laser surgery
JP2010538699A (en) * 2007-09-06 2010-12-16 アルコン レンゼックス, インコーポレーテッド Photodestructive treatment of the lens
US9456925B2 (en) * 2007-09-06 2016-10-04 Alcon Lensx, Inc. Photodisruptive laser treatment of the crystalline lens
WO2009036104A2 (en) * 2007-09-10 2009-03-19 Lensx Lasers, Inc. Effective laser photodisruptive surgery in a gravity field
US20090137993A1 (en) * 2007-09-18 2009-05-28 Kurtz Ronald M Methods and Apparatus for Integrated Cataract Surgery
WO2009039315A2 (en) * 2007-09-18 2009-03-26 Lensx Lasers, Inc. Methods and apparatus for laser treatment of the crystalline lens
WO2009059251A2 (en) * 2007-11-02 2009-05-07 Lensx Lasers, Inc. Methods and apparatus for improved post-operative ocular optical peformance
US20090177189A1 (en) 2008-01-09 2009-07-09 Ferenc Raksi Photodisruptive laser fragmentation of tissue
EP2248097A2 (en) * 2008-01-09 2010-11-10 Lensx Lasers, Inc. Ophthalmic surgical systems with automated billing mechanism
DE102008027358A1 (en) 2008-06-05 2009-12-10 Carl Zeiss Meditec Ag Ophthalmic laser system and operating procedures
US10182942B2 (en) 2008-06-05 2019-01-22 Carl Zeiss Meditec Ag Ophthalmological laser system and operating method
EP2349148A1 (en) * 2008-08-08 2011-08-03 Glostrup Hospital System and method for treatment of lens related disorders
DE102008049692B4 (en) * 2008-09-19 2010-05-12 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Laser-based device for non-contact scanning of eyes and corresponding laser-based scanning method
DE102009012873B4 (en) 2009-03-12 2021-08-19 Carl Zeiss Meditec Ag Ophthalmic laser system and control unit
US9054479B2 (en) * 2010-02-24 2015-06-09 Alcon Lensx, Inc. High power femtosecond laser with adjustable repetition rate
US20110206071A1 (en) * 2010-02-24 2011-08-25 Michael Karavitis Compact High Power Femtosecond Laser with Adjustable Repetition Rate
US8279901B2 (en) * 2010-02-24 2012-10-02 Alcon Lensx, Inc. High power femtosecond laser with adjustable repetition rate and simplified structure
US8953651B2 (en) * 2010-02-24 2015-02-10 Alcon Lensx, Inc. High power femtosecond laser with repetition rate adjustable according to scanning speed
DE102010022298A1 (en) * 2010-05-27 2011-12-01 Carl Zeiss Meditec Ag Apparatus and method for cataract surgery
US9579153B2 (en) 2010-06-03 2017-02-28 Carl Zeiss Meditec Ag Device and method for vitreous humor surgery
EP2392293B1 (en) 2010-06-04 2016-05-04 Carl Zeiss Meditec AG Intraocular lens provided for implantation into an eye and device for changing the optical effect of an implanted intraocular lens
DE102011109058A1 (en) 2011-07-29 2013-01-31 Carl Zeiss Meditec Ag "Ophthalmic Laser Device and Method for the Prevention and Treatment of After-Star"
US9050627B2 (en) 2011-09-02 2015-06-09 Abbott Medical Optics Inc. Systems and methods for ultrasonic power measurement and control of phacoemulsification systems
US8908739B2 (en) 2011-12-23 2014-12-09 Alcon Lensx, Inc. Transverse adjustable laser beam restrictor
US10548771B2 (en) 2012-09-06 2020-02-04 Carl Zeiss Meditec Ag Device and procedure to treat presbyopia
EP3300706B1 (en) * 2013-03-15 2019-04-24 AMO Development, LLC Varying a numerical aperture of a laser during lens fragmentation in cataract surgery
US10219948B2 (en) 2016-02-24 2019-03-05 Perfect Ip, Llc Ophthalmic laser treatment system and method
DE102016205914A1 (en) * 2016-04-08 2017-10-12 Carl Zeiss Meditec Ag Method for selective, minimally invasive laser therapy on the eye
WO2020058064A1 (en) 2018-09-20 2020-03-26 Carl Zeiss Meditec Ag Producing cuts in the interior of the eye
DE102019135607B4 (en) * 2019-12-20 2023-09-07 Schwind Eye-Tech-Solutions Gmbh Method for controlling an ophthalmic surgical laser and treatment device
US11877953B2 (en) 2019-12-26 2024-01-23 Johnson & Johnson Surgical Vision, Inc. Phacoemulsification apparatus
US11684799B2 (en) 2021-08-28 2023-06-27 Cutera, Inc. Image guided laser therapy

Citations (27)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4309998A (en) * 1978-06-08 1982-01-12 Aron Rosa Daniele S Process and apparatus for ophthalmic surgery
WO1987007165A1 (en) * 1986-05-19 1987-12-03 Automated Laser Systems, Inc. Precision laser system useful for ophthalmic surgery
US4907586A (en) 1988-03-31 1990-03-13 Intelligent Surgical Lasers Method for reshaping the eye
WO1993008677A2 (en) 1991-10-30 1993-05-13 Allergan, Inc. Method of laser photoablation of lenticular tissue for the correction of vision problems
US5280491A (en) * 1991-08-02 1994-01-18 Lai Shui T Two dimensional scan amplifier laser
US5312396A (en) * 1990-09-06 1994-05-17 Massachusetts Institute Of Technology Pulsed laser system for the surgical removal of tissue
WO1994025107A1 (en) 1993-04-20 1994-11-10 Novatec Laser Systems, Inc. Improved ophthalmic surgical laser and method
US5520679A (en) * 1992-12-03 1996-05-28 Lasersight, Inc. Ophthalmic surgery method using non-contact scanning laser
US5720894A (en) * 1996-01-11 1998-02-24 The Regents Of The University Of California Ultrashort pulse high repetition rate laser system for biological tissue processing
US5741245A (en) 1992-01-15 1998-04-21 Premier Laser Systems, Inc. Corneal sculpting using laser energy
DE19718139A1 (en) 1997-04-30 1998-11-05 Aesculap Meditec Gmbh Phaco-emulsification method for intra=ocular tissue removal
EP0903133A2 (en) 1997-08-21 1999-03-24 Escalon Medical Corp. Laser apparatus for intrastromal photorefractive keratectomy
US6156030A (en) * 1997-06-04 2000-12-05 Y-Beam Technologies, Inc. Method and apparatus for high precision variable rate material removal and modification
US6190374B1 (en) * 1996-11-29 2001-02-20 Nidek Co., Ltd. Apparatus for operating upon a cornea
US6197018B1 (en) 1996-08-12 2001-03-06 O'donnell, Jr. Francis E. Laser method for restoring accommodative potential
US6210401B1 (en) * 1991-08-02 2001-04-03 Shui T. Lai Method of, and apparatus for, surgery of the cornea
US6258082B1 (en) 1999-05-03 2001-07-10 J. T. Lin Refractive surgery and presbyopia correction using infrared and ultraviolet lasers
US6263879B1 (en) * 1998-11-10 2001-07-24 J. T. Lin Treatment of presbyopia and other eye disorders using a scanning laser system
US6322556B1 (en) 1991-10-30 2001-11-27 Arlene E. Gwon Method of laser photoablation of lenticular tissue for the correction of vision problems
US6325792B1 (en) 1991-11-06 2001-12-04 Casimir A. Swinger Ophthalmic surgical laser and method
US20010053906A1 (en) * 1998-03-04 2001-12-20 Marc Odrich Method and systems for laser treatment of presbyopia using offset imaging
USRE37504E1 (en) * 1992-12-03 2002-01-08 Lasersight Technologies, Inc. Ophthalmic surgery method using non-contact scanning laser
US20020103478A1 (en) * 1991-10-30 2002-08-01 Gwon Arlene E. Method of laser photoablation of lenticular tissue for the correction of vision problems
US6478792B1 (en) * 1999-09-03 2002-11-12 Carl Zeiss Jena Gmbh Method and apparatus for illumination of the eye
US6491688B1 (en) * 2000-06-21 2002-12-10 J. T. Lin Apparatus and methods for reversal of presbyopia using near infrared selective laser on zonnulas
US6514241B1 (en) * 1995-03-10 2003-02-04 Candela Corporation Apparatus and method for treating glaucoma using a gonioscopic laser trabecular ablation procedure
US20040199149A1 (en) * 1996-03-21 2004-10-07 Myers Raymond I. Lenticular refractive surgery of presbyopia, other refractive errors, and cataract retardation

Patent Citations (30)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4309998A (en) * 1978-06-08 1982-01-12 Aron Rosa Daniele S Process and apparatus for ophthalmic surgery
WO1987007165A1 (en) * 1986-05-19 1987-12-03 Automated Laser Systems, Inc. Precision laser system useful for ophthalmic surgery
US4907586A (en) 1988-03-31 1990-03-13 Intelligent Surgical Lasers Method for reshaping the eye
US5312396A (en) * 1990-09-06 1994-05-17 Massachusetts Institute Of Technology Pulsed laser system for the surgical removal of tissue
US6210401B1 (en) * 1991-08-02 2001-04-03 Shui T. Lai Method of, and apparatus for, surgery of the cornea
US5280491A (en) * 1991-08-02 1994-01-18 Lai Shui T Two dimensional scan amplifier laser
WO1993008677A2 (en) 1991-10-30 1993-05-13 Allergan, Inc. Method of laser photoablation of lenticular tissue for the correction of vision problems
US20020103478A1 (en) * 1991-10-30 2002-08-01 Gwon Arlene E. Method of laser photoablation of lenticular tissue for the correction of vision problems
US6322556B1 (en) 1991-10-30 2001-11-27 Arlene E. Gwon Method of laser photoablation of lenticular tissue for the correction of vision problems
US6325792B1 (en) 1991-11-06 2001-12-04 Casimir A. Swinger Ophthalmic surgical laser and method
US5741245A (en) 1992-01-15 1998-04-21 Premier Laser Systems, Inc. Corneal sculpting using laser energy
USRE37504E1 (en) * 1992-12-03 2002-01-08 Lasersight Technologies, Inc. Ophthalmic surgery method using non-contact scanning laser
US5520679A (en) * 1992-12-03 1996-05-28 Lasersight, Inc. Ophthalmic surgery method using non-contact scanning laser
US5984916A (en) * 1993-04-20 1999-11-16 Lai; Shui T. Ophthalmic surgical laser and method
WO1994025107A1 (en) 1993-04-20 1994-11-10 Novatec Laser Systems, Inc. Improved ophthalmic surgical laser and method
US6514241B1 (en) * 1995-03-10 2003-02-04 Candela Corporation Apparatus and method for treating glaucoma using a gonioscopic laser trabecular ablation procedure
US5720894A (en) * 1996-01-11 1998-02-24 The Regents Of The University Of California Ultrashort pulse high repetition rate laser system for biological tissue processing
US20040199149A1 (en) * 1996-03-21 2004-10-07 Myers Raymond I. Lenticular refractive surgery of presbyopia, other refractive errors, and cataract retardation
US6197018B1 (en) 1996-08-12 2001-03-06 O'donnell, Jr. Francis E. Laser method for restoring accommodative potential
US6190374B1 (en) * 1996-11-29 2001-02-20 Nidek Co., Ltd. Apparatus for operating upon a cornea
US20020013574A1 (en) 1997-04-30 2002-01-31 Jens Elbrecht Method and arrangement for phacoemulsification
DE19718139A1 (en) 1997-04-30 1998-11-05 Aesculap Meditec Gmbh Phaco-emulsification method for intra=ocular tissue removal
US6156030A (en) * 1997-06-04 2000-12-05 Y-Beam Technologies, Inc. Method and apparatus for high precision variable rate material removal and modification
US6482199B1 (en) 1997-06-04 2002-11-19 Joseph Neev Method and apparatus for high precision variable rate material, removal and modification
EP0903133A2 (en) 1997-08-21 1999-03-24 Escalon Medical Corp. Laser apparatus for intrastromal photorefractive keratectomy
US20010053906A1 (en) * 1998-03-04 2001-12-20 Marc Odrich Method and systems for laser treatment of presbyopia using offset imaging
US6263879B1 (en) * 1998-11-10 2001-07-24 J. T. Lin Treatment of presbyopia and other eye disorders using a scanning laser system
US6258082B1 (en) 1999-05-03 2001-07-10 J. T. Lin Refractive surgery and presbyopia correction using infrared and ultraviolet lasers
US6478792B1 (en) * 1999-09-03 2002-11-12 Carl Zeiss Jena Gmbh Method and apparatus for illumination of the eye
US6491688B1 (en) * 2000-06-21 2002-12-10 J. T. Lin Apparatus and methods for reversal of presbyopia using near infrared selective laser on zonnulas

Cited By (24)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7655002B2 (en) * 1996-03-21 2010-02-02 Second Sight Laser Technologies, Inc. Lenticular refractive surgery of presbyopia, other refractive errors, and cataract retardation
US9180051B2 (en) 2006-01-20 2015-11-10 Lensar Inc. System and apparatus for treating the lens of an eye
US8262646B2 (en) 2006-01-20 2012-09-11 Lensar, Inc. System and method for providing the shaped structural weakening of the human lens with a laser
US10842675B2 (en) 2006-01-20 2020-11-24 Lensar, Inc. System and method for treating the structure of the human lens with a laser
US9889043B2 (en) 2006-01-20 2018-02-13 Lensar, Inc. System and apparatus for delivering a laser beam to the lens of an eye
US9545338B2 (en) 2006-01-20 2017-01-17 Lensar, Llc. System and method for improving the accommodative amplitude and increasing the refractive power of the human lens with a laser
US20070185475A1 (en) * 2006-01-20 2007-08-09 Frey Rudolph W System and method for providing the shaped structural weakening of the human lens with a laser
US9375349B2 (en) 2006-01-20 2016-06-28 Lensar, Llc System and method for providing laser shot patterns to the lens of an eye
US8500723B2 (en) 2008-07-25 2013-08-06 Lensar, Inc. Liquid filled index matching device for ophthalmic laser procedures
US8708491B2 (en) 2008-07-25 2014-04-29 Lensar, Inc. Method and system for measuring an eye
US8480659B2 (en) 2008-07-25 2013-07-09 Lensar, Inc. Method and system for removal and replacement of lens material from the lens of an eye
US8758332B2 (en) 2009-07-24 2014-06-24 Lensar, Inc. Laser system and method for performing and sealing corneal incisions in the eye
US8617146B2 (en) 2009-07-24 2013-12-31 Lensar, Inc. Laser system and method for correction of induced astigmatism
US8465478B2 (en) 2009-07-24 2013-06-18 Lensar, Inc. System and method for performing LADAR assisted procedures on the lens of an eye
US8382745B2 (en) 2009-07-24 2013-02-26 Lensar, Inc. Laser system and method for astigmatic corrections in association with cataract treatment
US8556425B2 (en) 2010-02-01 2013-10-15 Lensar, Inc. Purkinjie image-based alignment of suction ring in ophthalmic applications
USD695408S1 (en) 2010-10-15 2013-12-10 Lensar, Inc. Laser system for treatment of the eye
US8801186B2 (en) 2010-10-15 2014-08-12 Lensar, Inc. System and method of scan controlled illumination of structures within an eye
USD694890S1 (en) 2010-10-15 2013-12-03 Lensar, Inc. Laser system for treatment of the eye
US10463541B2 (en) 2011-03-25 2019-11-05 Lensar, Inc. System and method for correcting astigmatism using multiple paired arcuate laser generated corneal incisions
US10716706B2 (en) 2011-04-07 2020-07-21 Bausch & Lomb Incorporated System and method for performing lens fragmentation
US9393154B2 (en) 2011-10-28 2016-07-19 Raymond I Myers Laser methods for creating an antioxidant sink in the crystalline lens for the maintenance of eye health and physiology and slowing presbyopia development
US9937078B2 (en) 2011-10-28 2018-04-10 Raymond I Myers Laser methods for creating an antioxidant sink in the crystalline lens for the maintenance of eye health and physiology and slowing presbyopia development
US8807752B2 (en) 2012-03-08 2014-08-19 Technolas Perfect Vision Gmbh System and method with refractive corrections for controlled placement of a laser beam's focal point

Also Published As

Publication number Publication date
WO2001013838A1 (en) 2001-03-01
DE50009739D1 (en) 2005-04-14
EP1212022B1 (en) 2005-03-09
EP1537841B1 (en) 2014-03-26
ATE290357T1 (en) 2005-03-15
US6726679B1 (en) 2004-04-27
EP1537841A2 (en) 2005-06-08
AU6703400A (en) 2001-03-19
DE19940712A1 (en) 2001-03-01
EP1537841A3 (en) 2005-09-07
EP1212022A1 (en) 2002-06-12

Similar Documents

Publication Publication Date Title
USRE40420E1 (en) Method and device for treating opaqueness and/or hardening of a closed eye
JP6388976B2 (en) Methods and equipment for precision machining of materials
KR102002634B1 (en) Apparatus for corneal crosslinking
JP5658649B2 (en) Equipment for precision processing of materials
US4309998A (en) Process and apparatus for ophthalmic surgery
CA2586214C (en) Apparatus and processes for preventing or delaying one or more symptoms of presbyopia
KR101294326B1 (en) Assembly and method for performing surgical laser treatments of the eye
EP2836175B1 (en) Laser device and process for configuring such laser device
CN109124871B (en) Laser assisted cataract surgery
US20120130357A1 (en) Low Wavefront Error Devices, Systems, and Methods for Treating an Eye
RU2469689C2 (en) Laser system for refraction surgery having sparing effect on eyes
Lubatschowski Ultrafast lasers in ophthalmology
Lubatschowski et al. Intrastromal refractive surgery by fs laser pulses
Linz et al. Laser Micro-and Nanostructuring for Refractive Eye Surgery
Lubatschowski Nonlinear tissue processing in ophthalmic surgery
Lubatschowski et al. Femtosecond Laser Fundamentals
Lubatschowski et al. Intrastromal refractive surgery using ultrashort laser pulses

Legal Events

Date Code Title Description
FEPP Fee payment procedure

Free format text: PAYOR NUMBER ASSIGNED (ORIGINAL EVENT CODE: ASPN); ENTITY STATUS OF PATENT OWNER: LARGE ENTITY

FPAY Fee payment

Year of fee payment: 8

FPAY Fee payment

Year of fee payment: 12