WO2002098335A1 - Dispositif et programme de determination de donnees de keratectomie - Google Patents
Dispositif et programme de determination de donnees de keratectomie Download PDFInfo
- Publication number
- WO2002098335A1 WO2002098335A1 PCT/JP2002/005452 JP0205452W WO02098335A1 WO 2002098335 A1 WO2002098335 A1 WO 2002098335A1 JP 0205452 W JP0205452 W JP 0205452W WO 02098335 A1 WO02098335 A1 WO 02098335A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- corneal
- data
- ablation
- eye
- eccentricity
- Prior art date
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/103—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining refraction, e.g. refractometers, skiascopes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/107—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining the shape or measuring the curvature of the cornea
-
- 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
- A61F9/00802—Methods or devices for eye surgery using laser for photoablation
- A61F9/00804—Refractive treatments
- A61F9/00806—Correction of higher orders
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/103—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining refraction, e.g. refractometers, skiascopes
- A61B3/1035—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining refraction, e.g. refractometers, skiascopes for measuring astigmatism
-
- 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
- A61F2009/00872—Cornea
-
- 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
- A61F2009/00878—Planning
- A61F2009/0088—Planning based on wavefront
Definitions
- the present invention relates to a corneal ablation data determination apparatus and a corneal ablation data determination program for a refractive surgery in which a corneal surface of a patient's eye (eye to be operated) is ablated (ablation) to correct a refractive error.
- Refractive surgery is known in which a cornea surface is excised with a laser beam in the ultraviolet wavelength range and its shape is changed to correct a refractive error in a patient's eye.
- Two methods are mainly used to calculate the amount of corneal ablation when correcting even the aberration of the eye by this operation.
- the amount of corneal ablation according to these conventional methods is determined for the emmetropic eye having no aberration in the measurement optical axis direction (or a specific refraction in the measurement optical axis direction) when measuring the objective refractive power distribution or the wavefront aberration distribution of the patient's eye.
- a stigmatic eye with power the human eye is an eccentric optical system composed of refractive elements such as the cornea and the crystalline lens, and the corneal shape is generally asymmetric with respect to the visual axis.
- the conventional method for calculating the amount of corneal ablation has a problem that the amount of ablation is uneven.
- the conventional corneal ablation method is With the method of calculating the amount of resection, an appropriate amount of corneal resection may not be obtained.
- the present invention has been made in view of the above-mentioned drawbacks of the prior art, and provides a corneal ablation data determination apparatus and a corneal ablation data determination program that can control the corneal ablation amount distribution and expand the ablation application range. Is a technical task. Disclosure of the invention
- the present invention is characterized by having the following configuration.
- a corneal ablation data determination device for a corneal ablation operation for correcting a refractive error by ablating a corneal surface includes input means for inputting measurement data of a wavefront difference distribution or a refractive power distribution of a patient's eye, An eccentric means for eccentricity of a reference axis as a reference for calculating a corneal ablation amount, and an arithmetic means for calculating an amount of corneal ablation based on measured data and eccentricity data of the reference axis are provided.
- the eccentric means Is characterized by including means for decentering the reference axis with respect to the measurement optical axis used for measuring the wavefront aberration distribution or refractive power distribution, and means for inputting the eccentricity data.
- the apparatus for determining corneal ablation data of (1) further includes means for inputting preoperative corneal shape data, and the calculating means includes: a preoperative corneal shape data, a measurement data, and a reference axis. It is characterized in that the postoperative corneal shape is determined based on the eccentricity data.
- the calculating means obtains the direction vector of the light incident on the cornea after the operation when the reference axis is decentered, and calculates the direction vector.
- Postoperative corneal shape based on It is characterized in that the condition (1) is determined as a normal vector of the cornea.
- FIG. 1 is a schematic configuration diagram of an optical system of a corneal ablation amount determining apparatus according to the present invention.
- FIG. 3 is a block diagram of a control system of the corneal ablation amount determination device.
- FIG. 5 is a diagram showing a screen example of a simulation map at the time of calculating the amount of corneal ablation.
- FIG. 6 is a diagram for explaining a case where additional resection is performed on a patient's eye after resection by irradiation with misalignment.
- BEST MODE FOR CARRYING OUT THE INVENTION hereinafter, an embodiment of the present invention will be described with reference to the drawings.
- FIG. 1 is a schematic configuration diagram of an optical system of a corneal ablation amount determining apparatus according to the present invention. The optical system is roughly classified into an eye refractive power measuring optical system, a fixation target optical system, and a corneal curvature measuring optical system.
- the eye refractive power measuring optical system 100 includes a slit light projecting optical system 1 and a slit image detecting optical system 10. Near-infrared light emitted from the light source 2 of the projection optical system 1 is reflected by the mirror 3 and illuminates the slit opening 4a of the rotating sector 14. Sector 4 is rotated by motor 5. The slit light scanned by the rotation of the sector 14 is reflected by the beam splitter 8 after passing through the projection lens 6 and the limiting aperture 7.
- the light passes through a beam splitter 9 having the same optical axis as above, is condensed near the cornea Ec of the patient's eye (examined eye, eye to be operated) E, and is projected on the fundus Ef.
- the light source 2 is disposed at a position conjugate with the vicinity of the cornea Ec with respect to the lens 6.
- the light receiving elements 15 a to 15 f are located on a straight line passing through the center of the light receiving surface (optical axis L 3), and the light receiving elements 15 a and 15 b and the light receiving elements 15 c and 15 d
- the light receiving elements 15 e and 15 f are provided so as to be symmetrical with respect to the center of the light receiving surface.
- the arrangement distances of these three pairs of light receiving elements are set so that the refractive power corresponding to each position in the meridian direction of the cornea E c can be detected (in FIG. 2, the equivalent size on the cornea is shown as the equivalent size on the cornea). Shown).
- the light receiving elements 15 g and 15 h are provided so as to be symmetrical about the optical axis L 3 on a straight line orthogonal to the straight line on which the light receiving elements 15 a to 15 f are arranged. ing.
- 30 is a fixation target optical system
- 31 is a visible light source
- 32 is a fixation target
- the corneal radius of curvature measuring optical system includes a radius of curvature measuring index projection optical system 25 and a radius of curvature measuring index detecting optical system 35.
- the projection optical system 25 has the following configuration.
- Reference numeral 26 denotes a conical braid plate having an opening in the center.
- a ring pattern having a large number of light-transmitting portions and light-shielding portions is formed concentrically around the optical axis L1.
- the illumination light emitted from the light source 27 is reflected by the reflector 28, and illuminates the bracket 26 almost uniformly from behind.
- the light of the ring pattern transmitted through the light-transmitting portion of the platinum plate 26 is projected on the cornea Ec, and forms a ring pattern (brachydling) image on the cornea Ec.
- the detection optics 3 5 includes the beam splitter 9 and the beam splitter 3
- FIG. 3 is a control system block diagram.
- the measurement system control section 50 includes light receiving elements 15a to 15h, a camera 38, a monitor 39, and a measurement switch 5.
- the monitor 39 is constituted by a touch panel and also serves as an input means.
- the control unit 50 is a refractive power calculation unit
- the computer 60 includes a control unit 61, a color display 62, a keyboard 63, a mouse 64, an FDD 66, and the like.
- the control unit 61 includes an arithmetic unit 61a and a memory 61b for storing a control program.
- the apparatus By operating the touch key of the monitor 39, the apparatus is set to the eye bending power measurement mode.
- the examiner performs alignment while observing the anterior segment image of the eye E on the monitor 39.
- the alignment projects an unillustrated index for alignment onto the cornea Ec from the front of the eye E so that the corneal reflection luminescent spot and the reticle have a predetermined positional relationship.
- the measurement optical axis (L 1) is aligned with the axis connecting the corneal reflection luminescent spot and the fixation target.
- the eye refractive power calculation unit 52 determines the level of the output signal from each light receiving element of the light receiving unit 14. An objective eye refractive power distribution is obtained based on the phase difference. First, a preliminary measurement is made in the same way as the refractive power of the conventional phase difference method. 3 Move 3 to perform fog on eye E. Then, based on the output signals of the light receiving elements 15g and 15h that change with the movement of the slit light (image) on the light receiving section 14, the light receiving elements 15a to 15f are positioned. Find the corneal vertex (corneal center) in the direction.
- the refractive power at the corneal site corresponding to each light receiving element is determined from the phase difference between the output signals of the light receiving elements 15a to 15f with respect to the corneal vertex (corneal center).
- the refracting power is calculated for each meridian at each angle step while rotating the projection optical system 1 and the light receiving section 14 by 180 degrees around the optical axis at a predetermined angle (1 degree) step.
- the distribution of refractive power that changes in the meridian direction is obtained (for details, see US Pat. No. 5,907,388 (JP-A-10-108837)).
- the eye refractive power value here is a value based on the corneal apex (center of the cornea), but can also be obtained as a refractive power value based on the position where the spectacle lens is worn.
- the obtained objective eye refractive power data is stored in the memory 55.
- the device When measuring the corneal curvature radius, the device is set to the corneal curvature radius measurement mode by operating the touch key of the monitor 39. After performing the same alignment as in the eye refractive power measurement mode, press the measurement switch 54 to perform measurement.
- the corneal shape calculation unit 53 performs image processing on the image captured by the camera 38 to detect the edge of the ring pattern image. Then, the corneal curvature radius is obtained by obtaining each edge position with respect to the corneal vertex (corneal center) at every predetermined angle (1 degree) step (for details, see US Pat. 7-124113) etc.). The obtained data of the corneal curvature radius is stored in the memory 55.
- the measurement data of the objective eye refractive power and the corneal shape is obtained as described above, the measurement data is input to the computer 60 via the floppy disk 59, and the keyboard 63 of the computer 60 is input.
- the amount of corneal ablation is calculated by manipulating the mouse 64 and the like. Below, keratotomy A method for calculating the removal amount will be described.
- Unit direction vector of refracted light in cornea pre Unit direction vector of light incident on cornea before correction post Unit direction vector of light incident on cornea after correction
- the vector Npre can be known by measuring the corneal shape.
- the vector Qpre is obtained by temporarily converting the above-described refractive power distribution measurement result into a wavefront aberration and obtaining the unit normal vector. be able to.
- any ray that leaves the eye through the fovea Although it does not intersect with the measurement optical axis, it is because the meridional component is obtained by measuring the refractive power distribution.
- Equation 4 is equivalent to Equation 1.
- Equation 3 the vector ⁇ post is obtained by Equation 3. Since the vector n Qc is already known and the vector Q post is a specified value, it can be solved for an unknown number of vectors Npost. Equation 3 is transformed as follows.
- the postoperative corneal shape condition can be obtained as a normal vector at each point.
- the vector Q post is expressed as an equation.
- the measurement optical axis of the eye refractive power measurement (and corneal shape measurement) is used as the reference coordinate, and the post-operative reference axis is subjected to a shift (shi ft) and an eccentricity of the tilt (tilt) therefrom.
- shi ft the measurement optical axis of the eye refractive power measurement
- tilt tilt
- FIG. 4 is a diagram showing how to set a coordinate system when eccentricity is added to the post-operative reference axis.
- the axis O Z is the measurement optical axis
- the axis P O ′ is the post-operation reference axis.
- sh i ft is specified by ⁇ X and ⁇ y
- t ilt is specified by ⁇ and ⁇ .
- the postoperative refractive power (Refract 1 ve Error) power u [diopterj] is targeted.
- N one x——
- Equation 17 Even if the corneal shape data obtained by the corneal shape measurement is obtained in a polar coordinate format, Expression 17 cannot be used directly.
- Equation 17 partial differentiation of the corneal height f P ( p , 0) with respect to 0 is required, so the radial position / 0 must be constant data. This is because p is the detection edge position of the ring pattern image and generally changes with the angle. Therefore, to obtain the normal vector Npre of the preoperative corneal shape, Equation 17 is used after converting into a polar coordinate data format in which P does not depend on the angle by interpolation. Alternatively, the expression is converted to the X-Y coordinate system and the expression 13 is used.
- Equation 22 is used to calculate the postoperative corneal shape. In the recurrence formula in the meridian direction,
- Equation 22 is the data interval in the radial direction perpendicular to the measurement optical axis of the measurement optical system shown in FIG.
- the amount of ablation at each point can be calculated by comparing the corneal shape data obtained by the corneal shape measurement in the region where the optical zone is set.
- the calculation unit 61a calculates the ablation amount under conditions based on the input data.
- a preoperative corneal shape force map 201 and a postoperative corneal shape force map 202 are displayed.
- the simulated ablation amount distribution is displayed in three dimensions.
- the display map 220 shows a shape map of the total resection amount, which is displayed as a difference between the height of the postoperative corneal shape and the height of the preoperative corneal shape.
- the display map 2 2 1 shows a shape map in which only spherical components (axially symmetric components) are extracted.
- the display map 222 shows a shape map in which only the cylindrical component (plane-symmetric component) is extracted.
- the shape map calculated and displayed first is simulated without inputting the eccentricity parameter, and that there are many irregular astigmatism components displayed on the display map 222 in a biased direction.
- the value of tilt is determined based on the position and magnitude of the bias of the irregular astigmatic component so as to reduce the irregular astigmatic component.
- the value of shift moves to the center of the pupil so as to match the axis at the time of abrasion.
- the post-operative corneal shape is calculated by the calculation unit 61a, and the result is displayed again on the screen 200 as a simulation map.
- the surgeon controls the distribution of the corneal ablation volume by such a simulation and determines whether or not the eccentricity of the reference axis for calculating the ablation volume is appropriate.
- the eccentricity of the reference axis for calculating the ablation amount is calculated not by the operator inputting the eccentricity parameter but by the calculating unit 61a so that the asymmetric irregular astigmatism component becomes smaller than a predetermined allowable value. May be determined automatically.
- the simulated ablation volume distribution if the postoperative corneal shape is good, this data can be recorded and stored on a floppy disk by the FDD 66 and used by the corneal surgery apparatus.
- the measurement optical axis direction 150 (this can be regarded as the ), The area is shifted, and the area 15 1 is replaced. Assuming that the measurement optical axis for the eye does not change from the state before the ablation, the calculation should be made so that the portion of the region 152 is ablated during the additional ablation.
- the measurement optical axis direction 150 this can be regarded as the .
- the measurement optical axis for the eye does not change from the state before the ablation
- the calculation should be made so that the portion of the region 152 is ablated during the additional ablation.
- a large portion of the already resected region 15 1 is to be resected, and the resection cannot be performed due to the corneal thickness.
- the apparatus for measuring the refractive power distribution of the eye is used, and the data of the corneal ablation amount is obtained from the measured data.
- the present invention can be applied to such cases.
- a light source image is projected on the fundus of the patient's eye, and reflected light from the fundus is imaged on an image sensor via a number of microlens arrays placed at conjugate positions with the pupil.
- a method of measuring the wavefront of the light refracted by the cornea of the patient's eye from the imaging information can be used (see USP. 6, 086, 204, etc.).
- the measurement of the refractive power distribution and the measurement of the wavefront aberration distribution differ in the expression form of the measurement results, but they both match in measuring the optical aberration of the eye.
- the vectors Q pre (operations) shown in Equations 2 and 5 above Since the vector in the unit direction of the light incident on the anterior cornea can be known through the wavefront aberration of the eye, the present invention is applied to calculate the corneal ablation amount even when measuring the wavefront aberration distribution. Can be.
- a method of calculating the amount of corneal ablation using an approximation formula known as an optical component processing technique based on the measurement of the wavefront aberration of the entire eye without using the corneal shape data (the approximation formula) Therefore, although the error in the peripheral part increases, the method of decentering the reference axis for calculating the ablation amount can control the ablation amount distribution.
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Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE60231806T DE60231806D1 (de) | 2001-06-01 | 2002-06-03 | Gerät zur bestimmung von keratektomie-daten |
EP02728224A EP1393700B1 (en) | 2001-06-01 | 2002-06-03 | Keratectomy data determining device |
US10/476,246 US7255440B2 (en) | 2001-06-01 | 2002-06-03 | Keratectomy data determining device and keratectomy data determining program |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2001-167325 | 2001-06-01 | ||
JP2001167325A JP4837840B2 (ja) | 2001-06-01 | 2001-06-01 | 角膜切除データ決定装置及び角膜切除データ決定プログラム |
Publications (1)
Publication Number | Publication Date |
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WO2002098335A1 true WO2002098335A1 (fr) | 2002-12-12 |
Family
ID=19009727
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/JP2002/005452 WO2002098335A1 (fr) | 2001-06-01 | 2002-06-03 | Dispositif et programme de determination de donnees de keratectomie |
Country Status (7)
Country | Link |
---|---|
US (1) | US7255440B2 (ja) |
EP (1) | EP1393700B1 (ja) |
JP (1) | JP4837840B2 (ja) |
CN (1) | CN1278661C (ja) |
AT (1) | ATE427087T1 (ja) |
DE (1) | DE60231806D1 (ja) |
WO (1) | WO2002098335A1 (ja) |
Families Citing this family (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP4330400B2 (ja) | 2003-08-04 | 2009-09-16 | 株式会社ニデック | 眼科装置 |
JP4492858B2 (ja) | 2004-07-20 | 2010-06-30 | 株式会社ニデック | 眼科装置及び眼内屈折力分布算出プログラム |
WO2013065805A1 (ja) * | 2011-11-02 | 2013-05-10 | 株式会社ニデック | 角膜撮影装置 |
KR101666107B1 (ko) * | 2012-04-20 | 2016-10-13 | 웨이브라이트 게엠베하 | 각막 절제 레이저를 제어하는 기술 |
US9839352B2 (en) | 2015-08-15 | 2017-12-12 | Smart EyeDeas I, LLC | System, method and apparatus for enabling corneal topography mapping by smartphone |
DE102016112023A1 (de) * | 2016-06-30 | 2018-01-04 | Carl Zeiss Ag | Komponente, Computerprogramm, System und Kit zur Augenglasbestimmung |
CN106344173A (zh) * | 2016-09-21 | 2017-01-25 | 爱博诺德(北京)医疗科技有限公司 | 用于角膜散光实时定位装置的光源 |
DE102020134038A1 (de) | 2020-12-17 | 2022-06-23 | Schwind Eye-Tech-Solutions Gmbh | Verfahren und Steuereinrichtung zum Bereitstellen von Steuerdaten eines augenchirurgischen Lasers zum Korrigieren einer bereits erfolgten Hornhautkorrektur an einer Hornhaut sowie Behandlungsvorrichtung |
CN113197543B (zh) * | 2021-05-06 | 2023-02-28 | 南开大学 | 基于矢量像差理论的屈光手术后视觉质量评价方法和系统 |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0836830A1 (en) * | 1996-10-03 | 1998-04-22 | Nidek Co., Ltd | Ophthalmic measurement apparatus |
EP0947158A1 (en) * | 1998-03-31 | 1999-10-06 | Nidek Co., Ltd. | Ophthalmic apparatus |
EP1034756A2 (en) * | 1999-03-10 | 2000-09-13 | Luis Antonio Ruiz, M.D. | Interactive corrective laser eye surgery system |
WO2001021061A1 (en) * | 1999-09-20 | 2001-03-29 | Magnante Peter C | Fabricate surfaces on contact lenses |
Family Cites Families (14)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE2614273C3 (de) * | 1976-04-02 | 1979-02-15 | Fa. Carl Zeiss, 7920 Heidenheim | Kombinationsgerät zur Augenuntersuchung |
US4666269A (en) * | 1982-08-09 | 1987-05-19 | Canon Kabushiki Kaisha | Ophthalmologic apparatus |
US5231674A (en) * | 1989-06-09 | 1993-07-27 | Lc Technologies, Inc. | Eye tracking method and apparatus |
DE4232915A1 (de) * | 1992-10-01 | 1994-04-07 | Hohla Kristian | Vorrichtung zur Formung der Cornea durch Abtragen von Gewebe |
JP3655020B2 (ja) * | 1996-08-01 | 2005-06-02 | 株式会社ニデック | 角膜手術装置 |
JP3916335B2 (ja) * | 1998-03-31 | 2007-05-16 | 株式会社ニデック | 角膜切除量決定装置及び角膜手術装置 |
KR100699403B1 (ko) * | 1998-10-02 | 2007-03-26 | 사이언티픽 오프틱스 인코포레이티드 | 시력 분석 및 개선 방법 |
WO2001024719A1 (en) * | 1999-10-05 | 2001-04-12 | Lasersight Technologies, Inc. | Ellipsoidal corneal modeling for estimation and reshaping |
ATE269042T1 (de) * | 1999-10-21 | 2004-07-15 | Nidek Kk | Vorrichtung zur bestimmung der menge der zu entfernenden kornea |
US6494577B2 (en) * | 2000-03-17 | 2002-12-17 | Canon Kabushiki Kaisha | Ophthalmologic apparatus |
JP3664937B2 (ja) * | 2000-03-27 | 2005-06-29 | 株式会社ニデック | 眼科装置 |
US20020049431A1 (en) * | 2000-10-20 | 2002-04-25 | Smith Michael J. | Method of correcting corneal refraction not aligned with the pupil center |
US6575572B2 (en) * | 2001-09-21 | 2003-06-10 | Carl Zeiss Ophthalmic Systems, Inc. | Method and apparatus for measuring optical aberrations of an eye |
DE60236226D1 (de) * | 2001-10-19 | 2010-06-10 | Bausch & Lomb | Verbesserung der Altersweitsichtigkeit |
-
2001
- 2001-06-01 JP JP2001167325A patent/JP4837840B2/ja not_active Expired - Fee Related
-
2002
- 2002-06-03 CN CNB028110021A patent/CN1278661C/zh not_active Expired - Fee Related
- 2002-06-03 US US10/476,246 patent/US7255440B2/en not_active Expired - Fee Related
- 2002-06-03 WO PCT/JP2002/005452 patent/WO2002098335A1/ja active Application Filing
- 2002-06-03 AT AT02728224T patent/ATE427087T1/de not_active IP Right Cessation
- 2002-06-03 DE DE60231806T patent/DE60231806D1/de not_active Expired - Lifetime
- 2002-06-03 EP EP02728224A patent/EP1393700B1/en not_active Expired - Lifetime
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0836830A1 (en) * | 1996-10-03 | 1998-04-22 | Nidek Co., Ltd | Ophthalmic measurement apparatus |
EP0947158A1 (en) * | 1998-03-31 | 1999-10-06 | Nidek Co., Ltd. | Ophthalmic apparatus |
EP1034756A2 (en) * | 1999-03-10 | 2000-09-13 | Luis Antonio Ruiz, M.D. | Interactive corrective laser eye surgery system |
WO2001021061A1 (en) * | 1999-09-20 | 2001-03-29 | Magnante Peter C | Fabricate surfaces on contact lenses |
Also Published As
Publication number | Publication date |
---|---|
US20040135969A1 (en) | 2004-07-15 |
EP1393700A1 (en) | 2004-03-03 |
EP1393700A4 (en) | 2006-10-11 |
EP1393700B1 (en) | 2009-04-01 |
US7255440B2 (en) | 2007-08-14 |
JP4837840B2 (ja) | 2011-12-14 |
JP2002355219A (ja) | 2002-12-10 |
DE60231806D1 (de) | 2009-05-14 |
CN1512861A (zh) | 2004-07-14 |
ATE427087T1 (de) | 2009-04-15 |
CN1278661C (zh) | 2006-10-11 |
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