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WO2007084579A2 - Système et appareil permettant de traiter le cristallin d'un oeil - Google Patents

Système et appareil permettant de traiter le cristallin d'un oeil Download PDF

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Publication number
WO2007084579A2
WO2007084579A2 PCT/US2007/001262 US2007001262W WO2007084579A2 WO 2007084579 A2 WO2007084579 A2 WO 2007084579A2 US 2007001262 W US2007001262 W US 2007001262W WO 2007084579 A2 WO2007084579 A2 WO 2007084579A2
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WO
WIPO (PCT)
Prior art keywords
lens
laser
eye
laser beam
determining
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.)
Ceased
Application number
PCT/US2007/001262
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English (en)
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WO2007084579A3 (fr
Inventor
Rudolph W. Frey
Gary P. Gray
Dennis R. Pape
George R. Downes, Jr.
Jorge A. De Castro
Jerome R. Kuszak
Neil Zepkin
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.)
Lensar Inc
Original Assignee
Lensar Inc
Lasersoft Vision Inc
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Filing date
Publication date
Priority claimed from US11/337,127 external-priority patent/US10842675B2/en
Application filed by Lensar Inc, Lasersoft Vision Inc filed Critical Lensar Inc
Publication of WO2007084579A2 publication Critical patent/WO2007084579A2/fr
Publication of WO2007084579A3 publication Critical patent/WO2007084579A3/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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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
    • A61F9/00—Methods 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
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/008—Methods or devices for eye surgery using laser
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00—Instruments, 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
    • A61B90/30—Devices for illuminating a surgical field, the devices having an interrelation with other surgical devices or with a surgical procedure
    • 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
    • A61F9/00—Methods 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
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/008—Methods or devices for eye surgery using laser
    • A61F9/00825—Methods or devices for eye surgery using laser for photodisruption
    • A61F9/00838—Correction of presbyopia
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B2018/2035—Beam shaping or redirecting; Optical components therefor
    • A61B2018/20351—Scanning mechanisms
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
    • A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
    • A61B2018/2035—Beam shaping or redirecting; Optical components therefor
    • A61B2018/20351—Scanning mechanisms
    • A61B2018/20355—Special scanning path or conditions, e.g. spiral, raster or providing spot overlap
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00—Instruments, 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
    • A61B90/36—Image-producing devices or illumination devices not otherwise provided for
    • A61B90/37—Surgical systems with images on a monitor during operation
    • A61B2090/371—Surgical systems with images on a monitor during operation with simultaneous use of two cameras
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00—Instruments, 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
    • A61B90/36—Image-producing devices or illumination devices not otherwise provided for
    • A61B90/361—Image-producing devices, e.g. surgical cameras
    • 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
    • A61F9/00—Methods 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
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/008—Methods or devices for eye surgery using laser
    • A61F2009/00861—Methods or devices for eye surgery using laser adapted for treatment at a particular location
    • A61F2009/0087—Lens
    • 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
    • A61F9/00—Methods 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
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/008—Methods or devices for eye surgery using laser
    • A61F2009/00885—Methods or devices for eye surgery using laser for treating a particular disease
    • A61F2009/00887—Cataract
    • 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
    • A61F9/00—Methods 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
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/008—Methods or devices for eye surgery using laser
    • A61F2009/00885—Methods or devices for eye surgery using laser for treating a particular disease
    • A61F2009/00887—Cataract
    • A61F2009/00889—Capsulotomy
    • 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
    • A61F9/00—Methods 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
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/008—Methods or devices for eye surgery using laser
    • A61F2009/00897—Scanning mechanisms or algorithms
    • 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
    • A61F9/00—Methods 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
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/008—Methods or devices for eye surgery using laser
    • A61F9/009—Auxiliary devices making contact with the eyeball and coupling in laser light, e.g. goniolenses

Definitions

  • FIG. 1 is a cross sectional view of the eye.
  • the sclera 131 is the white tissue that surrounds the lens 103 except at the cornea 101.
  • the cornea 101 is the transparent tissue that comprises the exterior surface of the eye through which light first enters the eye.
  • the iris 102 is a colored, contractible membrane that controls the amount of light entering the eye by changing the size of the circular aperture at its center (the pupil).
  • the ocular or natural crystalline lens 103 a more detailed picture of which is shown in FIGS. 1 A -F, (utilizing similar reference numbers for similar structures) is located just posterior to the iris 102.
  • the terms ocular lens, natural crystalline lens, natural lens, natural human crystalline lens, and lens are used interchangeably herein and refer to the same anatomical structure of the human eye.
  • the ocular lens changes shape through the action of the ciliary muscle 108 to allow for focusing of a visual image.
  • a neural feedback mechanism from the brain allows the ciliary muscle 108, acting through the attachment of the zonules 111 , to change the shape of the ocular lens.
  • sight occurs when light enters the eye through the cornea 101 and pupil, then proceeds through the ocular lens 103 through the vitreous 110 along the visual axis 104, strikes the retina 105 at the back of the eye, forming an image at the macula 106 that is transferred by the optic nerve 107 to the brain.
  • the space between the cornea 101 and the retina 105 is filled with a liquid called the aqueous 117 in the anterior chamber 109 and the vitreous 110, a gel-like clear substance, in the chamber posterior to the lens 103.
  • FIG.1A illustrates, in general, components of and related to the lens 103 for a typical 50-year old individual.
  • the lens 103 is a multi- structural system.
  • the lens 103 structure includes a cortex 113, and a nucleus 129, and a lens capsule 114.
  • the capsule 114 is an outer membrane that envelopes the other interior structures of the lens.
  • the lens epithelium 123 forms at the lens equatorial 121 generating ribbon-like cells or fibrils that grow anteriorly and posteriorly around the ocular lens.
  • the nucleus 129 is formed from successive additions of the cortex 113 to the nuclear regions.
  • the continuum of layers in the lens, including the nucleus 129 can be characterized into several layers, nuclei or nuclear regions.
  • the embryonic nucleus 122 is about 0.5 mm in equatorial diameter (width) and 0.425 mm in Anterior-Posterior axis 104 (AP axis) diameter (thickness).
  • the fetal nucleus 130 is about 6.0 mm in equatorial diameter and 3.0 mm in AP axis 104 diameter.
  • the infantile nucleus 124 is about 7.2 mm in equatorial diameter and 3.6 mm in AP axis 104 diameter.
  • the adolescent nucleus 126 is about 9.0 mm in equatorial diameter and 4.5 mm in AP axis 104 diameter.
  • the adult nucleus 128 at about age 36 is about 9.6 mm in equatorial diameter and 4.8 mm in AP axis 104 diameter.
  • this lens (nucleus and cortex) is about 9.8 mm in equatorial diameter and 4.9 mm in AP axis 104 diameter.
  • the structure of the lens is layered or nested, with the oldest layers and oldest cells towards the center.
  • the lens is a biconvex shape as shown in FIGS. 1 and 1A.
  • the anterior and posterior sides of the lens have different curvatures and the cortex and the different nuclei in general follow those curvatures.
  • the lens can be viewed as essentially a stratified structure that is asymmetrical along the equatorial axis and consisting of long crescent fiber cells arranged end to end to form essentially concentric or nested shells. The ends of these cells align to form suture lines in the central and paracentral areas both anteriorly and posteriorly.
  • the older tissue in both the cortex and nucleus has reduced cellular function, having lost their cell nuclei and other organelles several months after cell formation.
  • cataracts are areas of opacification of the ocular lens which are sufficient to interfere with vision.
  • Other conditions, for which the present invention Is directed, include but are not limited to the opacification of the ocular lens.
  • Presbyopia most often presents as a near vision deficiency, the inability to read small print, especially in dim lighting after about 40-45 years of age.
  • Presbyopia, or the loss of accommodative amplitude with age relates to the eyes inability to change the shape of the natural crystalline lens, which allows a person to change focus between far and near, and occurs in essentially 100% of the population.
  • Accommodative amplitude has been shown to decline with age steadily through the fifth decade of life.
  • the present specification postulates a different theory of how this loss of lens flexibility occurs to cause presbyopia.
  • the structure of the lens rather than the material properties of the lens plays a greater role in loss of flexibility and resultant presbyopia than was previously understood.
  • material elasticity is not the dominate cause of presbyopia. Rather, it is postulated that it is the structure of the lens and changes in that structure with age that is the dominant cause of presbyopia.
  • the present invention discloses a variety of methods and systems to provide laser treatments to increase the flexibility of the lens, based at least in part on the structure of the lens and structural changes that occur to the lens with aging.
  • the present invention further discloses providing laser treatments to increase the flexibility of the lens that are based primarily on the structure of the lens and structural changes that occur to the lens with aging.
  • accommodative Intraocular Lenses such as the Eyeonics CRYSTALENS, which are designed to change position within the eye; however, they offer only about 1 diopter of objectively measured accommodative amplitude, while many practitioners presently believe 3 or more diopters are required to restore normal visual function for near and far objects.
  • lOL's artificial accommodative Intraocular Lenses
  • researchers are pursuing techniques and materials to refill the lens capsule with synthetic materials.
  • present surgical techniques to implant artificial accommodative lOL's are those developed for the more serious condition of cataracts.
  • Refractive error typically due to the length of the eye being too long (myopia) or to short (hyperopia) is another very common problem effecting about one-half of the population.
  • Laser surgery on the cornea does offer effective treatment of refractive errors but factors such as higher degrees of refractive error, especially in hyperopia, thin corneas or a changing refractive error with time, such as that brought on by presbyopia, limit the clinical use of laser corneal surgery for many.
  • a system and apparatus for delivering a laser beam to a lens of an eye that utilize a laser, an optical path for directing a laser beam from the laser to the lens of the eye, a means for determining the shape and position of the lens with respect to a fixed point, and means for focusing a laser beam to a location in the lens of the eye, wherein that location was determined based at least in part upon data and/or information from the determining step.
  • a system and apparatus for delivering a laser beam in the lens of the eye in a predetermined shot pattern that utilize as series of shots that form a shell cut, a partial shell cut, a laser suture cut and/or a volumetric shaped removal, which essentially following the shape of a suture layer of the lens, i.e., a layer shape of the lens.
  • a system and apparatus for treating conditions of the lens comprising a laser, laser focusing optics, a scanner and a control system that has a plurality of means for directing in cooperation with the laser, the scanner and the laser focusing optics, laser shot patterns.
  • a system for delivering a laser to an eye and for obtaining stereo images of the eye comprising a laser, focusing optics, a scanner and a camera.
  • the scanner is optically associated with the laser and the camera so that the scanner has the capability to provide stereo pairs of images of the eye and deliver a laser beam from the laser to the eye.
  • a system and apparatus for treating conditions of the lens comprising: a laser, laser focusing optics, a scanner, a control system, a predetermined lens shot pattern, and a means for determining the position of the lens, wherein the means for determining may comprise a scanned laser illumination source, one or more cameras and/or a structured light source.
  • a system for delivering lasers to an eye and/or for obtaining stereo images of the eye comprising, a first laser for therapeutic purposes, i.e.
  • a therapeutic laser focusing optics, a camera, a second laser, serving as a laser illumination source, i.e., an illumination laser, and, a scanner optically associated with the first and second lasers and the camera; wherein the scanner has the capability to provide stereo pairs of images of the eye and deliver a laser beam from the first laser to the eye and deliver a laser beam from the second laser to the eye, is further provided.
  • a system for delivering a laser to an eye and for determining the position of the eye comprising a patient support, a laser, optics for delivering a laser beam, a control system for delivering the laser beam to the lens of the eye in a particular pattern, a lens position determination apparatus, and, a laser patient interface.
  • FIGS. 1 and 1A are cross sectional representations of the human eye.
  • FIG. 2 is a block schematic diagram of a type of system for delivering a laser beam shot pattern to the lens of an eye according to the teachings of the present invention.
  • FIG. 2A is a block schematic diagram of illustrative components forming a portion of a system for delivering a laser beam shot pattern to the lens of an eye according to the teachings of the present invention.
  • FIG. 2B is a block schematic diagram of illustrative components forming a portion of a system for delivering a laser beam shot pattern to the lens of an eye according to the teachings of the present invention.
  • FIG. 2C is a block schematic diagram of illustrative components forming a portion of a system for delivering a laser beam shot pattern to the lens of an eye according to the teachings of the present invention.
  • FIG. 2D is a block schematic diagram of illustrative components forming a portion of a system for delivering a laser beam shot pattern to the lens of an eye according to the teachings of the present invention.
  • FIG. 2E is a block schematic diagram of illustrative components forming a portion of a system for delivering a laser beam shot pattern to the lens of an eye according to the teachings of the present invention.
  • FIG. 3 is a diagram of the anterior surface of a lens normal to the AP axis illustrating a laser shot pattern having a flower like shape which has a contour generally following approximately the last 15% of the fiber length from the end of the fiber.
  • FIGS. 4A, 4B, 4C, 4D and 4E are diagrams representing elevation views of the geometry used ' for the development of laser shot patterns based upon the structure of the fetal nucleus (three suture branch nucleus) as it is rotated from the posterior view 4A through and to the anterior view 4E.
  • FIGS. 5A, 5B 1 and 5C are diagrams representing posterior, side and anterior elevation views, respectively, of the geometry used for the development of laser shot patterns based upon the structure of the infantile nucleus (six suture branch nucleus).
  • FIGS. 6A 1 6B and 6C are diagrams representing posterior, side and anterior elevation views, respectively of the geometry used for the development of laser shot patterns based upon the structure of the adolescent nucleus (nine suture branch nucleus).
  • FIGS. 7A, 7B and 7C are diagrams representing posterior, side and anterior elevation views, respectively of the geometry used for the development of laser shot patterns based upon the structure of the an adult nucleus (12 suture branch).
  • FIGS. 8 and 8A are perspective cutout views of an adult lens representing the placement of essentially concentric shells in accordance with the teachings of the present invention.
  • FIG. 9 is a cross-section drawing of the lens relating to the model developed by Burd.
  • FIG. 10 is a cross-section drawing of a lens based upon the model developed by Burd.
  • FIG. 11 is a cross-section drawing of a lens based upon the model developed by Burd.
  • FIG. 12 is a cross-section drawing of a lens based upon the model developed by Burd.
  • FIG. 13 is a cross-section drawing of a lens showing the placement of a shell laser shot pattern in accordance with the teachings of the present invention.
  • FIG. 14 is a cross-section drawing of a lens showing the placement of a shell laser shot pattern in accordance with the teachings of the present invention.
  • FIG. 15 is a cross-section drawing of a lens showing the placement of a partial shell laser shot pattern in accordance with the teachings of the present invention.
  • FIG. 16 is a cross-section drawing of a lens showing the placement of a partial shell laser shot pattern in accordance with the teachings of the present invention.
  • FIG. 17 is a cross-section drawing of a lens showing the placement of a shell laser shot pattern in accordance with the teachings of the present invention.
  • FIGS. 18 -24 are cross-section drawings of a lens showing the placement of a volumetric removal laser shot patterns in accordance with the teachings of the present invention.
  • FlG. 25 is a cross-section drawing of a lens showing the placement of a cube laser shot pattern in accordance with the teachings of the present invention.
  • FIGS. 26 -27 are cross-section drawings of a lens showing the placement of a gradient index modification laser shot patterns in accordance with the teachings of the present invention.
  • FIGS. 28 B, D, and F are diagrams illustrating the placement of the shot patterns of FIGS. 28 A, C, and E respectively.
  • FIG. 29 is a diagram illustrating the relative placement of the shot patterns of FIGS. 28 A, C, and E, if performed in the same lens.
  • FIGS. 30 A-D are diagrams of the cross-section of a lens illustrating a capsulomexis shot pattern of the present invention.
  • FIGS. 31 A-D are diagrams illustrating youthful vs old age gradient index behavior.
  • the present invention provides a system and method for increasing the amplitude of accommodation and/or changing the refractive power and/or enabling the removal of the clear or cataractous lens material of a natural crystalline lens.
  • a system for delivering a laser beam shot pattern to the lens of an eye comprising: a patient support 201; a laser 202; optics for delivering the laser beam 203; a control system for delivering the laser beam to the lens in a particular pattern 204, which control system 204 is associated with and/or interfaces with the other components of the system as represented by lines 205; a means for determining the position of lens with respect to the laser 206, which means 206 receives an image 211 of the lens of the eye; and a laser patient interface 207.
  • the patient support 201 positions the patent's body 208 and head 209 to interface with the optics for delivering the laser beam 203.
  • the laser 202 should provide a beam 210 that is of a wavelength that transmits through the cornea, aqueous and lens.
  • the beam should be of a short pulse width, together with the energy and beam size, to produce photodisruption.
  • laser shot or shot refers to a laser beam pulse delivered to a location that results in photodisruption.
  • photodisruption essentially refers to the conversion of matter to a gas by the laser.
  • wavelengths of about 300 nm to 2500 nm may be employed. Pulse widths from about 1 femtosecond to 100 picoseconds may be employed.
  • the pulse rate (also referred to as pulse repetition frequency (PRF) and pulses per second measured in Hertz) may be from about 1 KHz to several GHz.
  • PRF pulse repetition frequency
  • lower pulse rates correspond to higher pulse energy in commercial laser devices.
  • a wide variety of laser types may be used to cause photodisruption of ocular tissues, dependent upon pulse width and energy density. Thus, examples of such lasers would include: the Delmar Photonics Inc.
  • Trestles-20 which is a Titanium Sapphire (TirSapphire) oscillator having a wavelength range of 780 to 840 nm, less than a 20 femtosecond pulse width, about 100 MHz PRF, with 2.5 nanojoules; the Clark CPA-2161 , which is an amplified Ti:Sapphire having a wavelength of 775 nm, less than a 150 femtosecond pulse width, about 3 KHz PRF, with 850 microjouies; the IMRA FCPA (fiber chirped pulse amplification) ⁇ Jewel D series D-400-HR, which is a Yb:fiber oscillator/amplifier having a wavelength of 1045 nm, less than a 1 picosecond pulse width, about 5 MHz PRF, with 100 nanojoules; the Lumera Staccato, which is a Nd:YVO4 having a wavelength of 1064 nm, about 10 picosecond pulse width, about 100 KHz PRF, with 100 microjouies; and
  • the optics for delivering the laser beam 203 to the natural lens of the eye should be capable of providing a series of shots to the natural lens in a precise and predetermined pattern in the x, y and z dimension.
  • the optics should also provide a predetermined beam spot size to cause photodisruption with the laser energy reaching the natural lens.
  • the optics may include, without limitation: an x y scanner; a z focusing device; and, focusing optics.
  • the focusing optics may be conventional focusing optics, and/or flat field optics and/or telecentric optics, each having corresponding computer controlled focusing, such that calibration in x, y, z dimensions is achieved.
  • an x y scanner may be a pair of closed loop galvanometers with position detector feedback. Examples of such x y scanners would be the Cambridge Technology Inc. Model 6450, the SCANLAB hurrySCAN and the AGRES Rhino Scanner. Examples of such z focusing devices would be the Phsyik International Peizo focus unit Model ESee Z focus control and the SCANLAB varrioSCAN. [0058]
  • the control system for delivering the laser beam may be conventional focusing optics, and/or flat field optics and/or telecentric optics, each having corresponding computer controlled focusing, such that calibration in x, y, z dimensions is achieved.
  • an x y scanner may be a pair of closed loop galvanometers with position detector feedback. Examples of such x y scanners
  • control system 204 may be any computer, controller, and/or software hardware combination that is capable of selecting and controlling x y z scanning parameters and laser firing. These components may typically be associated at least in part with circuit boards that interface to the x y scanner, the z focusing device and/or the laser.
  • the control system may also, but does not necessarily, have the further capabilities of controlling the other components of the system as well as maintaining data, obtaining data and performing calculations. Thus, the control system may contain the programs that direct the laser through one or more laser shot patterns.
  • the means for determining the position of the lens with respect to the laser 206 should be capable of determining the relative distance with respect to the laser and portions of the lens, which distance is maintained constant by the patient interface 207.
  • this component will provide the ability to determine the position of the lens with respect to the scanning coordinates in all three dimensions. This may be accomplished by several methods and apparatus. For example, x y centration of the lens may be accomplished by observing the lens through a co-boresighed camera system and display or by using direct view optics and then manually positioning the patients' eye to a known center.
  • the z position may then be determined by a range measurement device utilizing optical triangulation or laser and ccd system, such as the Micro-Epsilon opto NCDT 1401 laser sensor and/or the Aculux Laser Ranger LR2-22 .
  • a 3-dimensional viewing and measurement apparatus may also be used to determine the x, y and z positions of the lens.
  • the Hawk 3 axis non-contact measurement system from Vision Engineering could be used to make these determinations.
  • an apparatus that can be used to determine the position of the lens is a 3-dimension measurement apparatus. This apparatus would comprise a camera, which can view a reference and the natural lens, and would also include a light source to illuminate the natural lens. Such light source could be a structured light source, such as for example a slit illumination designed to generate 3-dimensional information based upon geometry.
  • a further component of the system is the laser patient interface 207.
  • This interface should provide that the x, y, z position between the natural lens and the laser remains fixed during the procedure, which includes both the measurement steps of determining the x y z position and the delivery step of delivering the laser to the lens in a shot pattern.
  • the interface device may contain an optically transparent applanator.
  • One example of this interface is a suction ring applanator that is fixed against the outer surface of the eye and is then positioned against the laser optical housing, thus fixing the distance between the laser, the eye and the natural lens. Reference marks for the 3-dimensional viewing and measuring apparatus may also be placed on this applanator.
  • a further example of a laser patient interface is a device having a lower ring, which has suction capability for affixing the interface to the eye.
  • the interface further has a flat bottom, which presses against the eye flattening the eye's shape.
  • This flat bottom is constructed of material that transmits the laser beam and also preferably, although not necessarily, transmits optical images of the eye within the visible light spectrum.
  • the upper ring has a structure for engaging with the housing for the laser optics and/or some structure that is of known distance from the laser along the path of the laser beam and fixed with respect to the laser.
  • the interface may be a corneal shaped transparent element whereby the cornea is put into direct contact with the interface or contains an interface fluid between.
  • FIG. 2A An illustrative combination utilizing by way of example specific optics for delivering the laser beam 203 and means for determining the position of the lens 206, is shown in part, in FIG. 2A.
  • FIG. 2A is a more detailed schematic diagram of a configuration of the system of FIG. 2.
  • FIG. 2A provides a laser 202, laser optics for delivering the laser beam 203, which optics comprise a beam expander telescope 220, a z focus mechanism 221 , a beam combiner 222, an x y scanner 223, and focusing optics 224.
  • relay optics 230 camera optics 231 , which may also include a zoom, and a ccd camera 232, which components form a part of a three-dimensional viewing and measuring apparatus.
  • these components 231 and 232 in combination with a light source 233, and the scanner 223 are the means for determining the position of the lens 206.
  • FIG. 2A utilizes the x y scanner 223 to create stereoscopic images of the lens with only a single ccd camera 232.
  • Optical images 211 of the eye 213 and in particular optical images of the natural lens 103 of the eye 213 are conveyed along a path 211.
  • This path 211 follows the same path as the laser beam 210 from the natural lens 103 through the laser patient interface 207, the focusing optics 224, the x y scanner 223 and the beam combiner 222.
  • This combination of FIG. 2A further comprises: a laser patient interface 207, and a light source 233, which could be for example uniform illumination, or a slit illumination or other structured light source designed to enhance 3-d ⁇ mensional accuracy.
  • the light source in part, provides illumination of the natural lens of the patient's eye for the purposes of determining the 3-dimensional position of the lens.
  • a controller and/or computer not shown in FIG. 2A for further processing and use in determining 3-dimensional positions of the lens.
  • Stereo images may be generated by commanding the scanner to go to and pause at a nominal left position and then electronically trigger the camera and controller to capture and store the left image; then command the scanner/camera/controller similarly to capture and store a right image. This sequence may be repeated in a periodic manner.
  • These left and right images can be processed by the controller to generate the position and shape of the lens.
  • the left and right images can be displayed using a stereo video monitor.
  • Camera images or stereo images may also be used to measure suture geometry and orientation in the patients lens, which can be used to determine the parameters of suture based shot patterns and to align suture based shot patterns to the patients lens suture geometry and orientation.
  • the combination illustrated in FIG. 2A provides 3-dimensional information that can be used to determine the shape of the lens, including the anterior and posterior surfaces thereof. This information can also be used to visualize the structure of the lens, including sutures. Moreover, the information about the lens obtained from the combination of FIG. 2A can further be used in determining the laser shot pattern and laser shot placement with respect to lens
  • FIGS. 2 and 2A-2E are block schematic diagrams and thus the relative positions and spacing of the components illustrated therein are by way of example. Accordingly, the relative placements of these components with respect to one another may be varied and all or some of their functions and components may be combined.
  • FIGS. 2B-2E are further more detailed embodiments of a portion of the system of FIG. 2. To the extent that like numbers are used in these Figures and in FIG. 2 and 2A they have the same meaning. Thus, FIGS. 2B-2E provide further examples and combinations of optics for delivering the laser beam 203 and means for determining the position of the lens 206.
  • FIG. 2B is a block schematic diagram of a portion of a system having a means for determining the position of the lens 206, which employs a scanned laser illumination source.
  • a laser illumination source 235 a beam expander and focusing optics 236, an illumination laser path 237 and a camera 238 for viewing the lens 103 as illuminated by the laser illumination source.
  • Component 235 in combination with the scanner 223 and camera 238 are the means for detecting the position of the lens 206.
  • the laser illumination source 235 can be any visible or near infrared laser diode, preferably with a short coherence length for reduced speckle.
  • the laser can be a Schafter+Kirchhoff Laser (90CM- M60-780-5-Y03-C-6) or can also be obtained from StockerYale and may also come with focusing optics.
  • x y scanner 223 scans the beam from the illumination laser 235 into the focusing optics 224, through the patient interface 207 and onto the lens 103.
  • the beam from the illumination laser 235 follows the illumination laser path 237.
  • the beam expander focusing optics 236 combined with focusing optics 224 provide a high F number, slow focusing beam with long depth of field.
  • the depth of field is approximately equal to the path length of the laser illumination beam through the lens 103.
  • the illumination laser beam is scanned, predominately in one axis, in a line at a rate sufficiently fast compared to the camera 238 exposure time such that the scanned illumination laser beam acts like a slit illumination source during the exposure time.
  • the illumination laser beam is scanned to different positions, thus, illuminating the entire lens over time. This can occur as a series of y scanned lines with different x positions exposures or the lines can be radially scanned with each exposure at a different angle.
  • the three-D position and shape of the anterior and posterior surfaces and the spatial distribution of the scattering amplitude of the lens material between those surfaces can be determined.
  • This information may be processed by the control system and used for screening patients and implementing laser shot patterns.
  • FIG. 2C is a block schematic diagram of a portion of a system having a means for detecting the position of the lens 206, which employs dual cameras. Thus, there is provided a left camera 241 and a right camera 242. Components 241 , 242 and 233 are the means for detecting the position of the lens 206.
  • the system of FIG. 2C utilizes two camera stereo viewing technology for providing patient care capability and for obtaining images and data for determining lens position and/or shape. From the analysis of the data from the images thus obtained, the three-D position and shape of the anterior and posterior surfaces and the spatial distribution of the scattering amplitude of the lens material between those surfaces can be determined. This information may be processed by the control system and used for screening patients and implementing laser shot patterns.
  • FIG. 2D is a block schematic diagram of a portion of a system having a means for detecting the position of the lens 206, which employs structured illumination.
  • Components 245 and 246 in combination are a means for detecting the position of the lens 206.
  • the system of FIG. 2D utilizes a structured light source and a camera to provide patient care capability and for obtaining images and data for determining lens position and/or shape. From the analysis of the data from the images thus obtained, the three-D position and shape of the anterior and posterior surfaces and the spatial distribution of the scattering amplitude of the lens material between those surfaces can be determined. This information may be processed by the control system and used for screening patients and implementing laser shot patterns.
  • FIG. 2E is a block schematic diagram of a portion of a system having a means for detecting the position of the lens 206, which employs structured illumination and dual cameras.
  • Components 245 and 246, in combination are the means for detecting the position of the lens 206.
  • Components 241 and 242, in combination are a means for providing patient care, including monitoring capability. This combination 241 , 242 may also provide information and/or data to determine the position of the lens.
  • Patient care includes, but is not limited to, visualization of the eye and its surrounding area, procedures such as attaching a suction ring, applying ophthalmic drops, utilizing instruments, and positioning the patient for surgery.
  • the structured light source 245 may be a slit illumination having focusing and structured light projection optics, such as a Schafter+Kirchhoff Laser Macro Line Generator Model 13LTM+90CM, ⁇ Type 13LTM-250S-41 + 90CM-M60-780-5-Y03-C-6) or a StockerYale Model SNF-501L-660-20-5.
  • the structured illumination source 245 also includes scanning means.
  • Another embodiment of the structured light source 245, may be a stationary grid pattern projected on the lens. From the analysis of the data from the images thus obtained, the three-D position and shape of the anterior and posterior surfaces and the spatial distribution of the scattering amplitude of the lens material between those surfaces can be determined. This information may be processed by the control system and used for screening patients and implementing laser shot patterns.
  • the operation includes positioning the slit on one side of the lens, taking an image then moving the slit approximately one slit width, then taking another image, and then repeating this sequence until the entire lens is observed.
  • a 100 ⁇ m slit width can scan a nominal 9 mm dilated pupil diameter in 90 images, which takes approximately 3 seconds using a 30 Hz frame rate camera.
  • the slit should be at an angle to the AP axis, i.e., it should not be parallel to that axis.
  • the nominal slit angle can be approximately 15 to 30 degrees from the AP axis.
  • any visible or near IR wavelength source within the sensitivity of the camera may be used.
  • Low coherence length sources are preferable to reduce speckle noise.
  • Another embodiment for the structured light illumination subsystem shown in fig. 2E is to arrange the structured light illumination source 245, the structured light camera 246 and the lens for the structured light camera 247 in the so-called Scheimpflug configuration which is well-known.
  • the Scheimpflug condition states that given an object, a lens and an image, that the object plane is imaged sharply in the image plane if the object plane, the lens plane and the image plane intersect in the same line.
  • the structured light source 245 projects a line and or a plurality of lines onto the eye lens 103 at an angle or plurality of angles.
  • the light scattered at the eye lens 103 forms the object to be imaged by the lens 247 and focused onto the camera system 246. Since the slit illuminated image in the eye lens 103 may be at a large angle with respect to the camera lens 247 and camera 246, this presents a large depth of field to the camera and the entire slit image may not be in sharp focus at the camera. By tilting the camera lens and the camera at an angle or plurality of angles such that Scheimpflug's condition is met, the image along the illuminated plane can be in sharp focus.
  • the camera and/or lens may be tilted such that the angle between the slit illuminated image plane and the camera focal plane is reduced, improving the dept-of-focus sharpness, however may not meet the Scheimpflug condition.
  • Such configurations can improve sharpness further by reducing the aperture of the optical path, thereby increasing the F# of the system. These angles will depend on the angle the slit beam makes with the eye. This will increase the depth of field at the object, the scattered light from the slit illuminator, and allow it to imaged through the lens onto the camera image plane and remain in focus for the entire depth of the object.
  • a structured light illuminating and receiving system such as for example slit illumination, which in addition to measuring the position and shape of anterior and posterior lens surfaces in three dimensions, can be used as a screening tool for determining a candidate patient's suitability for laser lens surgery.
  • a structured light illuminating and receiving system such as for example slit illumination
  • slit illumination which in addition to measuring the position and shape of anterior and posterior lens surfaces in three dimensions, can be used as a screening tool for determining a candidate patient's suitability for laser lens surgery.
  • Such scattering malformations of the lens would include, without limitation, cataractous, pre- cataractous and non-cataractous tissue. Such scattering malformations, may be located throughout the lens, or may be restricted to specific regions of the lens.
  • the systems of FIGS 2A — 2E in cooperation with a controller and/or processor may function as such a structured light illuminating and receiving system.
  • the structured light illuminating and receiving system may be contained within the surgical laser system or it may be a separate unit for evaluating the suitability of a candidate patient for laser lens surgery.
  • Commercially available examples of such structured light illuminating and receiving systems are the Ziemer Ophthalmic Systems GALILEI Dual Scheimpflug Analyzer and the Oculus, Inc. PENTACAM. It is believed that these systems cannot be used to determine the position of the lens with respect to the treatment laser. However, lens shape data from these systems may be obtained and then used in conjunction with position data provided by systems such as the systems of FIGS. 2A -2E.
  • laser lens surgery may be indicated or contra-indicated for a particular patient's lens.
  • certain shot patterns, and/or combinations and placement of shot patterns may be indicated or contra-indicated, depending upon the location of the malformations, the shot patterns, the placement of the shot patterns and the intended effect of the shot pattern. Malformations that would substantially interfere with the desired effect of a laser shot pattern would make that laser shot pattern contra-indicated.
  • laser surgery in the anterior of that particular lens would be indicated, for example a pattern such as that shown in FIG. 20, while laser surgery in the posterior would be contra-indicated, such as the patterns shown in FIG. 21.
  • FIGS. 4 A -E illustrate the three branched or Y suture geometry in the context of the structures found in the fetal nucleus 415 of the lens.
  • these figures provide a more detailed view of the structures illustrated as layer 130, which encompasses layer 122 of FIG. 1A.
  • the view of the inner layer of the lens is rotated stepwise from the posterior side FIG. 4A to the anterior side FIG. 4E of the lens.
  • this layer of the lens has three posterior suture lines 401, 402, and 403.
  • This layer also has three anterior suture lines 412, 413 and 414.
  • the anterior suture lines are longer than the posterior suture lines and these lines are staggered when viewed along the anterior to posterior (AP) axis 411.
  • the lens fibers, which form the layers of the nucleus are shown by lines 404, it being understood that these are only illustrative lines and that in the actual natural layer of the lens there would be many times more fibers present.
  • lines 404 To aid in illustrating the structure and geometry of this layer of the nucleus representative fibers 405, 406, 407, 408, 409 and 410 have been exaggerated and individually shaded in FIGS. 4 A-E.
  • FIGS. 4 A-E Thus, as the view of the lens nucleus is rotated from posterior to anterior the positions of these representative fibers, there relationship to each other, and there relationship to the suture lines is illustrated.
  • the length of the suture lines for the anterior side are approximately 75% of the equatorial radius of the layer or shell in which they are found.
  • the length of the suture lines for the posterior side are approximately 85% of the length of the corresponding anterior sutures, i.e, 64% of the equatorial radius of that shell.
  • the term - essentially follows — as used herein would describe the relationship of the shapes of the outer surface of the lens and the fetal nucleus 415.
  • the fetal nucleus is a biconvex shape.
  • the anterior and posterior sides of the lens have different curvatures, with the anterior being flatter. These curvatures generally follow the curvature of the cortex and the outer layer and general shape of the lens.
  • the lens can be viewed as a stratified structure consisting of long crescent fiber cells arranged end to end to form essentially concentric or nested shells.
  • the present invention utilizes this and the further addressed geometry, structure and positioning of the lens layers, fibers and suture lines to provide laser shot patterns for increasing the accommodative amplitude of the lens.
  • it is the structure, positioning and geometry of the lens and lens fibers, in contrast to the material properties of the lens and lens fibers, that gives rise to loss of accommodative amplitude.
  • these patterns are designed to alter and affect that structure, positioning and/or geometry to increase accommodative amplitude.
  • FIGS. 5A-C illustrate the six branched or star suture geometry in the context of the structure found in the infantile layer of the nucleus 515 of the lens.
  • FIGS. 5A - C provide a more detailed view of the structures illustrated as layer 124 of FIG. 1A.
  • the view of the layer of the lens is rotated from the posterior side FIG. 5A to a side view FIG. 5B to the anterior side FIG. 5C.
  • this layer of the nucleus has six posterior suture lines 501, 502, 503, 504, 505, and 506.
  • This layer of the nucleus also has six anterior suture lines 509, 510, 511 , 512, 513, and 514.
  • the anterior suture lines are longer than the posterior suture lines and these lines are staggered when viewed along the AP axis 508.
  • the lens fibers, which form the layers of the nucleus, are shown by lines 507, it being understood that these are only illustrative lines and that in the actual natural layer of the lens there would be many times more fibers present.
  • the shape of the outer surface of the lens essentially follows the infantile nucleus 515, which is a biconvex shape.
  • the anterior and posterior sides of this layer of the lens have different curvatures, with the anterior being flatter. These curvatures generally follow the curvature of the cortex and the outer layer and general shape of the lens.
  • the lens can be viewed as a stratified structure consisting of long crescent fiber cells arranged end to end to form essentially concentric or nested shells, with the infantile nucleus 515 having the fetal nucleus 415 nested within it.
  • additional fiber layers grow containing between 6 and 9 sutures.
  • FIGS. 6A-C illustrate the nine branched or star suture geometry in the context of the structure found in the adolescent layer of the nucleus 611 of the lens.
  • FIGS. 6A - C provide a more detailed view of the structures illustrated as layer 126 of FIG. 1A.
  • the view of the layer of the lens is rotated from the posterior side FIG. 6A to a side view FIG. 6B to the anterior side FIG. 6C.
  • this layer of the nucleus has nine posterior suture lines 601 , 602, 603, 604, 605, 606, 607, 608 and 609.
  • This layer of the nucleus also has nine anterior suture lines 612, 613, 614, 615, 616, 617, 618, 619 and 620.
  • the anterior suture lines are longer than the posterior suture lines and these lines are staggered when viewed along the AP axis 610.
  • the lens fibers, which form the layers of the nucleus, are shown by lines 621 ; it being understood that these are only illustrative lines, and that in the actual natural layer of the lens there would be many times more fibers present.
  • the outer surface of the cornea follows the adolescent nucleus 611 , which is a biconvex shape.
  • the anterior and posterior sides of this layer have different curvatures, with the anterior being flatter.
  • These curvatures generally follow the curvature of the cortex and the outer layer and general shape of the lens.
  • These curvatures also generally follow the curvature of the fetal nucleus 415 and the infantile nucleus 515, which are nested within the adolescent nucleus 611.
  • the lens can be viewed as a stratified structure consisting of long crescent fiber cells arranged end to end to form essentially concentric or nested shells. As development continues through adulthood, additional fiber layers grow containing between 9 and 12 sutures.
  • FIGS. 7A-C illustrates the twelve branched or star suture geometry in the context of the structure found in the adult layer of the nucleus 713 of the lens.
  • FIGS. 7A - C the view of the layer of the lens is rotated from the posterior side FIG. 7A to a side view FIG. 7B to the anterior side FIG. 7C.
  • the adult layer of the nucleus has twelve posterior suture lines 701 , 702, 703, 704, 705, 706, 707, 708, 709, 710, 711 , and 712.
  • This layer of the nucleus also has twelve anterior suture lines 714- 725.
  • the anterior suture lines are longer than the posterior suture lines and these lines are staggered when viewed along the AP axis 726.
  • the lens fibers, which form the layers of the nucleus, are shown by lines 728; it being understood that these are only illustrative lines, and that in the actual natural layer of the lens there would be many times more fibers present.
  • the adult nucleus 713 is a biconvex shape that follows the outer surface of the lens.
  • the anterior and posterior sides of this layer have different curvatures, with the anterior being flatter.
  • These curvatures follow the curvature of the cortex and the outer layer and shape of the lens.
  • These curvatures also generally follow the curvature of the adolescent nucleus 611, the infantile nucleus 515 and the fetal nucleus 415 and the embryonic nucleus, which are essentially concentric to and nested within the adult nucleus 611.
  • the lens can be viewed as a stratified structure consisting of long crescent fiber cells arranged end to end to form essentially concentric or nested shells.
  • a subsequent adult layer having 15 sutures may also be present in some individuals after age 40.
  • This subsequent adult layer would be similar to the later adult layer 713 in general structure, with the recognition that the subsequent adult layer would have a geometry having more sutures and would encompass the later adult layer 713; and as such, the subsequent adult layer would be the outermost layer of the nucleus and would thus be the layer further from the center of the nucleus and the layer that is youngest in age.
  • the present invention provides for the delivery of the laser beam in patterns that utilize, or are based at least in part on, the lens suture geometry and/or the curvature of the lens and/or the various layers within the nucleus; and/or the curvatures of the various layers within the nucleus; and/or the suture geometry of the various layers within the nucleus.
  • the concept of matching the curvature of the anterior ablations to the specific curvature of the anterior capsule, while having a different curvature for posterior ablations, which in turn match the posterior curvature of the lens is provided.
  • Anterior and posterior curvatures can be based on Kuszak aged lens models, Burd's numeric modeling, Burd et al.
  • these laser delivery patterns are based in whole and/or in part on the mathematical modeling and actual observation data regarding the shape of the lens, the shape of the layers of the lens, the suture pattern, and the position of the sutures and/or the geometry of the sutures.
  • these laser delivery patterns are based in whole and/or in part on the mathematical modeling and actual observation data regarding the shape of the lens, the shape of the layers of the lens, the suture pattern, and the position of the sutures and/or the geometry of the sutures.
  • laser beam delivery patterns that cut a series of essentially concentric, i.e., nested, shells in the lens may be employed.
  • the shells would essentially follow the anterior and posterior curvature of the lens.
  • creating in the lens a series of cuts which resemble the nucleus layers of FIGS. 4, 5, 6 and 7. These cuts may follow the same geometry, i.e., shape and distance from the center, of these layers or may follow only a part of that geometry.
  • the adult nucleus 128 and cortex 113 are also provided.
  • shell refers to the lens material and the term shell cut refers to the laser beam delivery pattern and consequently the placement of the laser beam shots in the lens in accordance with that pattern. More or less shell cuts, and thus shells may be utilized.
  • the cuts may be such that they in effect create a complete shell, i.e., the shell and shell cuts completely encompass a volume of lens material.
  • the cuts may also be such that less than a complete shell is formed.
  • the creation of partial shells, by the use of partial shell cuts may be employed.
  • Such partial cuts would for example be only a portion of a shell e.g., the anterior quartile, the anterior half, the posterior quartile, stacked annular rings, staggered annular rings, and/or combinations thereof.
  • Such partial shells and shell cuts may be any portion of a three dimensional form, including ellipsoid, spheroids and combinations thereof as those terms are used in their broadest sense that in general follows the contours of the lens, capsule, cortex, nucleus, and/or the layers of the lens'including the layers of the nucleus.
  • the use of complete and partial shells and shell cuts may be used in a single lens.
  • the first and second cuts 801 and 803 are annular cuts, while the third cut is a complete cut.
  • partial shells are created, by use of partial pie shaped shell cuts. These cuts may be placed in between the suture lines at the various layers of the lens. These partial shells may follow the contour of the lens, i.e., have a curved shape, or they may be flatter and have a more planar shape or be flat.
  • a further use of these pie shape shells and shell cuts would be to create these cuts in a suture like manner, but not following the natural suture placement in the lens.
  • a suture like pattern of cuts is made in the lens, following the general geometry of the natural lens suture lines, but not their exact position in the lens.
  • other shaped cuts may be employed, such as by way of illustration a series of ellipses, rectangular planes or squares.
  • a further use of partial shells and/or planar partial shells is to create a series of overlapping staggered partial shells by using overlapping staggered partial shell cuts. In this way essentially complete and uninterrupted layers of lens material are disrupted creating planar like sections of the lens that can slide one atop the other to thus increase accommodative amplitude.
  • These partial shells can be located directly atop each other, when viewed along the AP axis, or they could be slightly staggered, completely staggered, or any combination thereof.
  • lines can also be cut into the lens. These lines can follow the geometry and/or geometry and position of the various natural suture lines.
  • a laser shot pattern places shots in the geometry of one or more of the natural suture lines of one or more of the various natural layers of the lens as shown in FIGS. 4, 5, 6, and 7, as well as in the 15 suture line layer, or it may follow any of the other patterns in the continuum of layers in the lens.
  • These shot patterns can follow the general geometry of the natural suture lines, i.e., a series of star shapes with the number of legs in each star increasing as their placement moves away from the center of the lens.
  • These star shaped shot patterns may follow the precise geometry of the natural suture patterns of the layers of the lens; or it can follow the exact geometry and placement of the sutures, at the same distances as found in the natural lens or as determined by modeling of the natural lens.
  • one or more stars may be cut.
  • the length of the lines of the legs of the star may be the longer, shorter or the same length as the natural suture lines. Moreover, if the length is shorter than the natural length of the suture lines, it may be placed toward the center of the star shape, i.e. the point where the lines join each other, or towards the end of the suture line, i.e., the point furthest on the suture line from the joining point. Further, if the cut is towards the end of the suture line it may extend beyond the suture line or may be co- terminus therewith.
  • partial star shaped cuts can be used, such as cuts having a "V" shape, or vertical or horizontal or at an angle in between. These linear cuts, discussed above, are in general referred to herein as laser created suture lines. Moreover, laser created suture lines may be grouped together to in effect form a shell or partial shell.
  • a shot pattern 301 is provided to an anterior portion of a layer 302 of the lens.
  • This shot pattern 301 has a contour 303 that follows the contour of approximately the last 15% of fiber length of fibers, represented by lines 304.
  • the shell cut resembles the shape of a flower.
  • the number of petals in the flower shaped shell should correspond to the number of suture lines 305 at that growth layer.
  • this partial shell cut and/or cuts will have the effect of unbinding the layers and returning the lens to a more youthful increased amplitude of accommodation.
  • annular partial shells or planar partial shells in this general area i.e., the general area at or near the ends of the suture lines, may be employed for the same reasons.
  • This theory is put forward for the purposes of providing further teaching and to advancing the art. This theory, however, is not needed to practice the invention; and the invention and the claims herein are not bound by or restricted by or to this theory.
  • laser created suture lines including star shaped patterns may also be used in conjunction with shells, partial shells and planar partial shells.
  • a particular laser shot pattern, or series of shot patterns employing elements of each of these shapes. These patterns may be based upon the geometry shown in FIGS. 4 -7 as well as the 15 suture line geometry discussed herein; they may follow that geometry exactly, in whole or in part; and/or they may follow that geometry, in whole or in part, as well as following the position of that geometry in the lens.
  • a maximum of 15 suture lines is known in the natural lens, more than 15 laser created suture lines may be employed.
  • the lens has multiple layers with a continuum of suture lines ranging from 3 to 15 and thus, this invention is not limited to the suture patents of FIGS. 4-7, but instead covers any number of suture lines from 3 to 15, including fractions thereof.
  • the delivery of shot patterns for the removal of lens material is further provided.
  • a shot pattern that cuts the lens into small cubes, which cubes can then be removed from the lens capsule is provided.
  • the cubes can range in size from a side having a length of about 100 ⁇ m to about 4 mm, with about 500 ⁇ m to 2 mm being a preferred size.
  • this invention is not limited to the formation of cubes and other volumetric shapes of similar general size may be employed.
  • the laser is also used to create a small opening, capsulorhexis, in the lens anterior surface of the lens capsule for removal of the sectioned cubes.
  • this procedure may be used to treat cataracts.
  • This procedure may also be used to remove a lens having opacification that has not progressed to the point of being cataractous.
  • This procedure may further be used to remove a natural lens that is clear, but which has lost its ability to accommodate.
  • a suitable replacement such as an 1OL, accommodative IOL, or synthetic lens refilling materials.
  • the size and the shape of the capsulorhexis is variable and precisely controlled and preferably is in 2 mm or less diameter for lens refilling applications and about 5 mm for lOLs.
  • a further implementation of the procedure to provide a capsulorhexis is to provide only a partially annular cut and thus leave a portion of the capsule attached to the lens creating a hinged flap like structure. Thus, this procedure may be used to treat cataracts.
  • volumetric removal of the lens can be performed to correct refractive errors in the eye, such as myopia, hyperopia and astigmatism.
  • the laser shot pattern is such that a selected volume and/or shape of lens material is removed by photodisruption from the lens.
  • volumetric removal of lens tissue can be preformed in conjunction with the various shot patterns provided for increasing accommodative amplitude. In this manner both presbyopia and refractive error can be addressed by the same shot pattern and/or series of shot patterns.
  • the volumetric removal of lens tissue finds further application in enhancing corrective errors for patients that have had prior corneal laser visions correction, such as LASIK, and/or who have corneas that are too thin or weak to have laser corneal surgery.
  • the laser shot patterns generally follow the shape of the lens and placement of individual shots with respect to adjacent shots in the pattern are sufficiently close enough to each other, such that when the pattern is complete a sufficiently continuous layer and/or line and/or volume of lens material has been removed; resulting in a structural change affecting accommodative amplitude and/or refractive error and/or the removal of lens material from the capsule. Shot spacing of lesser or greater distances are contemplated herein and including overlap as necessary to obtain the desired results. Shot spacing considerations include gas bubble dissipation, volume removal efficiency, sequencing efficiency, scanner performance, and cleaving efficiency among others.
  • the term cleaving means to substantially separate the tissue.
  • the forgoing shot spacing considerations are interrelated to a lesser or greater extent and one of skill in the art will know how to evaluate these conditions based upon the teachings of the present disclosure to accomplish the objectives herein.
  • the placement of individual shots with respect to adjacent shots in the pattern may in general be such that they are as close as possible, typically limited by the size and time frame of photodisruption physics, which would include among other things gas bubble expansion of the previous shot.
  • the time frame of photodisruptive physics referrers to the effects that take place surrounding photodisruption, such as plasma formation and expansion, shock waive propagation, and gas bubble expansion and contraction.
  • the timing of sequential pulses such that they are timed faster than some of, elements of, or all of those effects, can increase volumetric removal and/or cleaving efficiency. Accordingly, we propose using pulse repetition frequencies from 50 MHz to 5 GHz., which could be accomplished by a laser with the following parameters: a mode lock laser of cavity length from 3 meters to 3 cm. Such high PRF lasers can more easily produce multiple pulses overlapping a location allowing for a lower energy per pulse to achieve photodisruption. [00100]
  • the terms first, second, third, etc. as used herein are relative terms and must be viewed in the context in which they are used. They do not relate to timing, unless specifically referred to as such. Thus, a first cut may be made after a second cut.
  • Burd modeling which model is set forth in Burd et al., Numerical modeling of the accommodating lens, Visions Research 42 (2002) 2235-2251.
  • the Burd model provides the following algorithm for anterior and/or posterior shape:
  • FIGS. 10, 11 and 12 provide cross sectional views of the lens having an outer surface 1001 , 1101 , 1201 for three ages, 18, 29 and 45-year old respectively, based upon the Burd model and show growth in size along with shape changes with age.
  • the units for the axes on these drawings, as well as for FIGS. 13 to 29 are in millimeters (mm).
  • EXAMPLE 1 provides for making nested, lens shaped shell cuts.
  • the laser shot patterns are illustrated in FIG. 13, which provides the outer surface 1301 of a 45-year old lens based upon the Burd model.
  • a series of nested or essentially concentric shells and shell cuts which essentially follow the shape of the lens.
  • These shell cuts form a first shell 1303 and a second shell 1305.
  • Shells or partial shells are designed to increase flexibility in the lens by decreasing the strength of nested fiber layers by separating the bound layers, which it is theorized would reduce the structural strength and increase deflection for a given load or force.
  • the shell cuts in this example are positioned approximately such that the third shell cut 1306 is where 3 suture branches begin forming additional branches, or approximately 6 mm lens equatorial diameter, at the boundary of the fetal nucleus, or the lens at birth; the second shell cut 1304 is where the 6 suture branch layer begins forming additional branches at approximately 7.2 mm diameter, or the infantile nucleus or the lens at approximately age 3; and the first shell cut is where the 9 suture branch begins forming additional branches at approximately 9 mm diameter, or at the adolescent nucleus at approximately age 13.
  • EXAMPLE 2 provides as an alternative to using a 45-year old lens shape from the Burd model, the actual patient lens structural or shape data may be utilized to customize surgery for each patient.
  • a 45-year old human cadaver lens whose shape was measured optically and mathematically fit via the same fifth order function used in the Burd model, yields coefficients unique to the measured lens.
  • the outer cross- section shape of this lens and a shot pattern similar to that of Example 1, but which was tailored to the particular lens of this Example is illustrated in FIG 14.
  • an outer surface 1401 of the 45-year old lens There is further provided a series of nested or essentially concentric shells and shell cuts.
  • first shell cut 1402 a first shell cut 1402, a second shell cut 1404, and a third shell cut 1406. These shell cuts form a first shell 1403 and a second shell 1405. It is further noted that any of the exemplary cuts and shot patterns can be implemented via partial or full shells and/or can be implemented via modeled (the Burd model being just one example) or measured lens data.
  • EXAMPLE 3 provides a shot pattern for cutting partial shells on the measured 45-year old lens, and having an excluded defined central zone.
  • an outer surface 1501 of a 45-year old lens a central zone 1512
  • partial cuts 1502, 1504, 1506, 1507, 1509 and 1511 This also provided partial shells 1503, 1505, 1508 and 1510.
  • These partial cuts as shown are part of the same generally a ⁇ nularly shaped.
  • cuts 1502 and 1507, cuts 1504 and 1509, and cuts 1506 and 1511 are the opposite sides respectively of three generally annularly shaped partial.
  • EXAMPLE 4 provides a shot pattern for cutting partial shells on the measured 45-year old lens, and having both an excluded defined peripheral zone and central zone.
  • an outer surface 1601 of a 45-year old lens a central zone 1622 and two peripheral zones 1620 and 1621.
  • partial cuts 1602, 1604, 1605, 1606, 1607, 1611 , 1613, 1615, 1617, and 1618 as well as, partial shells 1603, 1608, 1609, 1610, 1612, 1614, 1616 and 1619.
  • these cuts are viewed in cross section and thus it is understood that they are opposite sides of generally annular ring shaped cuts, which essentially follow the shape of the lens and which encompasses the central zone 1622.
  • EXAMPE 5 provides a laser shot pattern for a finer detailed cutting of the lens to approximate the structural boundaries at 3, 4, 5, 6, 7, 8, 9 suture branches, or the use of six shells.
  • FIG. 17 seven essentially concentric shot patterns 1702 - 1708, which create seven corresponding shell cuts and which also create six corresponding shells 1709- 1714.
  • the outer surface 1701 of a 45-year old lens as measured is also provided in FIG. 17. While this example provides for the creation of six shells, it is understood that the lens contains thousands of fiber layers and that it may be desirable to utilize much greater than six shells and up to hundreds or even thousands, depending on the resolution of the laser deliver system and laser beam parameters.
  • Examples 6-12 relate to the volumetric removal of lens material in a predetermined shape, based upon a precise shot pattern. Thus, these examples illustrate how refractive change by shaped volumetric reduction may be accomplished.
  • This approach recognizes a limitation of photodissruption laser beam delivery, i.e., that the gas bubbles created are considerably larger then the resultant material void found after all gas bubble dissipation occurs. This can have the effect of causing material voids to be spaced further apart than ideal for high efficiency volume removal.
  • the closest spacing attainable depending on detailed laser spot size, energy and pulse width, may provide a low, net volumetric removal efficiency, which is the ratio of achieved volume removal to the volume of material treated.
  • a simple example considers a void size equal to the spacing between voids yielding a nominal 50% linear efficiency, which from symmetric geometry has a 25% area efficiency and a corresponding 12.5% volumetric efficiency of void creation.
  • an approach is provided whereby the treatment shaped volume is proportionally larger than desired shaped volume removal to compensate for the low volume efficiency.
  • void shape asymmetries, void location, tissue compliance as a function of age, external forces and more, may effect the final volume efficiency and experimental validation of volumetric efficiency may be required.
  • EXAMPLE 6 provides a shot pattern and volume removal to make a negative refractive change, or reduce the power in the crystalline lens by 3 Diopters, using the Gullstrand-LaGrand optical model, which would require the removal of approximately 180um centrally tapering to 0 over a 3mm radius.
  • FIG. 18 there is provided _an outer lens surface 1801 and a shot pattern 1802 for the desired volume removal.
  • the shot pattern would have to remove essentially 100% of the shaded region volume which is extremely difficult due to low volume efficiency found in photodissruption laser beam delivery.
  • EXAMPLE 7 is based upon dealing with low volume removal efficiency and in this example the assumption that we have a volumetric efficiency of 12.5% or 1/8 th we would treat an 8 times larger volume or 1.44mm thick to compensate for the low volume efficiency, tapering to 0 over the same 3mm as shown in FIG. 19, which illustrates a lens outer surface 1901 and a shot pattern 1902. As with the prior examples the shape of the shot pattern is based upon and essentially follows the shape of the outer surface 1901 of the lens.
  • EXAMPLE 8 provides a shot pattern to cause a refractive change to increase lens power or reduce hyperopia in patients, where the shot pattern is primarily implemented in the anterior region of the lens. This pattern is illustrated in FIG. 20, which provides an outer surface 2001 and thus shape of the lens and a shot pattern 2002.
  • EXAMPLE 9 provides a shot pattern to cause a refractive change to increase lens power or reduce hyperopia in patients, where the algorithm is primarily implemented in the posterior region of the lens.
  • This pattern is illustrated in FIG. 21 , which provides an outer surface 2101 and thus shape of the lens and a shot pattern 2102.
  • This example further illustrates a shot pattern having a shape is modified to primarily follow the posterior curve of the lens.
  • EXAMPLE 10 provides a shot pattern to cause a refractive change to increase lens power or reduce hyperopia in patients, where the shot pattern is primarily implemented in the central region of the lens.
  • the shot pattern is primarily implemented in the central region of the lens.
  • an outer surface 2201 of the lens and a shot pattern 2202, which provides a volumetric shape.
  • the anterior shape of the lens or posterior shape of the lens or both can be utilized to determine the shape of the shot pattern and/or volumetric shape.
  • EXAMPLE 11 provides two volumetric shot patterns that follow the shape of the lens surface to which they are adjacent.
  • the volumetric shapes to be removed from the lens are located in the anterior and posterior regions of the lens and have a surface that follows the anterior and posterior shape of the lens respectively.
  • EXAMPLE 12 illustrates a manner in which different shot pattern features are combined to address both refractive errors and those to increase flexibility utilizing a plurality of stacked partial shells, which are partially overlapping.
  • the placement of the partial shell cuts are adjacent the anterior surface of the lens as shown it FIG. 24.
  • the partial shell cuts may similarly be placed adjacent the posterior surface of the lens, in which case they should follow the shape of that surface.
  • 6,7,8,9,10 and 11 are shown to cut horizontal partial planes whose extent is defined by a refractive shape. It is to be understood that as an alternative to horizontal planes, vertical partial planes or other orientation cuts whose extent is defined by the refractive shape may be used.
  • Examples 13 and 14 are directed towards methods and shot patterns for treating and removal of cataracts and/or for clear lens extractions.
  • a method for the structural modification of the lens material to make it easier to remove while potentially increasing the safety of the procedure by eliminating the high frequency ultrasonic energy used in Phaco emulsification today.
  • the use of photodissruption cutting in a specific shape patterns is utilized to carve up the lens material into tiny cube like structures small enough to be aspirated away with 1 to 2 mm sized aspiration needles.
  • EXAMPLE 13 provides a shot pattern to create 0.5mm sized cubes out of the lens material following the structural shape of a 45-year old Burd Model lens. It is preferred that the patient's actual lens shape can be measured and used.
  • an outer surface 2501 and thus an outer shape of the lens.
  • a shot pattern 2502 that creates grid like cuts, the end of which cuts 2503 essentially follows the shape of the lens.
  • the sequence of laser shots in the pattern in FIG. 25 may be executed from posterior to anterior, as in most of the patterns disclosed herein, to obtain more predictable results by reducing the variation caused by shooting through gas bubbles.
  • EXAMPLE 14 provides for a clear lens extraction.
  • the shot pattern of FIG. 25 is applied to a clear lens and that lens material is subsequently removed.
  • shooting from posterior to anterior is desirable.
  • EXAMPE 15 provides for a precision capsulorhexis.
  • the creation of precise capsulorhexis for the surgeon to access the lens to remove the lens material is provided.
  • an outer surface 3001 and thus an outer shape of the lens.
  • a ring shaped band shape cut 3002 and shot pattern are provided.
  • the figure shows the cross section view of this ring shaped annular band and accordingly provides for two sides 3002 of the ring.
  • the ring shaped capsulorhexis cuts of 100 ⁇ m deep, approximately centered on the anterior lens capsule surface and precisely 5mm in diameter.
  • the lens capsule is approximately 5 to 15 ⁇ m thick, it is desirable for the depth of the cut to be typically between 5 and several hundred um, although there is not much penalty for cutting several millimeters.
  • This diameter can be varied between 0.1mm to 9mm diameter and the capsulorhexis can be elliptical with the x axis different then the y axis or other shapes.
  • a particular IOL may benefit from and/or may require a particular capsulorhexis shape.
  • Examples 16 to 17 relate to gradient index modification of the lens.
  • Moffat, Atchison and Pope, Vision Research 42 (2002) 1683-1693 showed that the natural crystalline lens contains a gradient index of refraction behavior that follows the lens shells structure and dramatically contributes to overall lens power. They also showed that this gradient substantially diminishes, or flattens as the lens ages reducing the optical power of the lens.
  • the loss of gradient index with age most likely explains the so-called Lens Paradox, which presents the conundrum that the ageing lens is known to grow to a steeper curvature shape that should result in higher power, yet the aging lens has similar power to the youthful lens. Essentially it is postulated that the increase in power due to shape changes is offset by the power loss from gradient index loss.
  • FIG. 31 Examples of the youthful vs old age gradient index behavior is shown in FIG. 31, which provides data taken from the more recent work from the same group Jones, Atchison, Meder and Pope, Vision Research 45 (2005) 2352-236.
  • the old lens 3101 has a flat index behavior radially 3102 and the young lens 3103 has continuously diminishing index radially 3104 from approximately 1.42 in the center to 1.38 nearer the outer shells of the lens.
  • the photodissruptive laser in the creation of small voids within the lens fiber material which will then fill-in with aqueous humor fluid which has a lower index of refraction and, via area weighting or volume weighting, decrease the net refractive index of a particular region. Accordingly, if different void densities are placed in nested shell volumes, then this would diminish the average index of refraction of essentially concentric regions in a similar manner to the youthful lens.
  • EXAMPLE 16 provides a gradient index modification, which has different void densities placed in nested volumes, as shown in Figure 26.
  • a series of nested shot patterns 2602 and a lens outer surface 2601 with each pattern creating an incrementally different void density in the lens material. For example, if a nominal 25% weighting efficiency was obtained in the most densely treated region, filling that volume with 1.38 index of aqueous humor, and the remaining region that was 75% lens material of index 1.42, then the average resultant index of refraction would be 0.25 * 1.38 + 0.75*1.42 or 1.41 , which we see from FIG. 31 , that would restore the gradient from the center to a 2mm radius, which is most central optical region for visual function.
  • FIG. 26 shows a distributed regional treatment of increasing density from the center of the lens to the periphery of the lens.
  • EXAMPLE 17 provides a gradient index modification that is similar to example 16, except that the area where void density is changed is located further from the outer surface of the lens.
  • This example and pattern is illustrated in FIG. 27.
  • FIG. 27 Thus there is provided a series of nested shot patterns 2702 and lens outer surface 2701 , with each pattern creating an incrementally different void density in the lens material.
  • this figure shows a distributed regional shell treatment that is primarily confined to the nucleus.
  • EXAMPLE 18 provides for the cutting in relation to suture lines. Thus, cuts along either modeled suture lines, according to Kuzak described suture locations as a function of shell geometry with age and shape, or measured suture lines may be used.
  • FIGS 28 & 29 shows three different cutting patterns 2801 , 2802, 2803 in the anterior portion of the lens that can be done separately or in combination.
  • Figures 28 A, C & E shows x-y cuts 2801, 2802, 2803 looking down at the anterior side of the lens.
  • FIGS. 28 B, D, and F are schematic representation to illustrate that the star shaped patterns follow the shape of the layer of the lens and do not show the actual cut.
  • FIG. 29 is the combination of the illustrations in FIGS. 28 B, D, and F to show their relative positions. It is understood that similar suture cuts can be made in the posterior following the posterior shell curves there, based again on either modeled geometry or measured lens data. There is yet further provided cutting 3,4,5,6,7,8,9,10,11 ,12,13,14 and 15 branch sutures per Kuszak., cut separately or in any combination.
  • a system for performing these examples, or parts of these examples may include by way of illustration and without limitation a laser, an optical system for delivering the laser beam, a scanner, a camera, an illumination source, and an applanator. These components are positioned so that when the eye is illuminated by the illumination source, light will travel from the eye through the applanator to the scanner. In this system the illumination source is movable with respect to the eye to provide varying angles by which the eye can be illuminated.
  • such system may also include by way of example and without limitation a laser, a system for determining the position and shape of components of an eye, a camera, a controller (which term refers to and includes without limitation processors, microprocessors and/or other such types of computing devices that are known to those of skill in the art to have the capabilities necessary to operate such a system), an illumination source, and an eye interface device.
  • the scanner is optically associated with the eye interface device, such that when the eye is illuminated by the illumination source, light will travel from the eye through the eye interface device to the scanner.
  • the scanner is further optically associated with the camera, such that the scanner has the capability to provide stereo pairs of images of the eye to the camera.
  • the camera is associated with the controller and is capable of providing digital images of the eye to the controller; and, the controller further has the capability to determine, based in part upon the digital images provided from the camera, the shape, position and orientation of components of the eye.
  • such systems may also include by way of example and without limitation a system for delivering a laser to an eye.
  • This system would have a laser, a scanner, a camera, an illumination source, an eye interface device, a means for determining the shape and position of components within an eye and a means for directing the delivery of a laser beam from the laser to a precise three dimensional coordinate with respect to the components of the eye, the means for directing the delivery of the laser beam having the capability to direct the beam based at least in part on the determination of the shape and position of components within the eye by the determining means.

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Abstract

L'invention concerne un système et un appareil permettant d'augmenter l'amplitude d'accommodation et/ou de changer la puissance de réfraction et/ou de permettre de retirer la substance du cristallin claire ou cataractée d'un cristallin naturel. En général, le système comprend un laser, des éléments optiques permettant d'administrer le faisceau laser et un système de commande permettant d'administrer le faisceau laser dans le cristallin selon un motif spécifique. L'invention concerne également un appareil permettant de déterminer la forme et la position du cristallin par rapport au laser. L'invention concerne enfin un procédé et un système permettant d'administrer un faisceau laser dans le cristallin de l'oeil selon un motif de décharge prédéterminé.
PCT/US2007/001262 2006-01-20 2007-01-18 Système et appareil permettant de traiter le cristallin d'un oeil Ceased WO2007084579A2 (fr)

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US11/337,127 US10842675B2 (en) 2006-01-20 2006-01-20 System and method for treating the structure of the human lens with a laser
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US11/414,819 US9180051B2 (en) 2006-01-20 2006-05-01 System and apparatus for treating the lens of an eye

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Cited By (2)

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US8911431B2 (en) 2008-06-05 2014-12-16 Carl Zeiss Meditec Ag Ophthalmological laser system and operating method
US10182942B2 (en) 2008-06-05 2019-01-22 Carl Zeiss Meditec Ag Ophthalmological laser system and operating method

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US5098426A (en) * 1989-02-06 1992-03-24 Phoenix Laser Systems, Inc. Method and apparatus for precision laser surgery
US6099522A (en) * 1989-02-06 2000-08-08 Visx Inc. Automated laser workstation for high precision surgical and industrial interventions

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Publication number Priority date Publication date Assignee Title
US8911431B2 (en) 2008-06-05 2014-12-16 Carl Zeiss Meditec Ag Ophthalmological laser system and operating method
US10182942B2 (en) 2008-06-05 2019-01-22 Carl Zeiss Meditec Ag Ophthalmological laser system and operating method
US10744037B2 (en) 2008-06-05 2020-08-18 Carl Zeiss Meditec Ag Ophthalmological laser system and operating method

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