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
  • A61F9/00825—Methods or devices for eye surgery using laser for photodisruption
  • A61F9/00831—Transplantation
• • 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
• • 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
  • 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
  • A61F9/00836—Flap cutting
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
  • A61B2017/00017—Electrical control of surgical instruments
  • A61B2017/00022—Sensing or detecting at the treatment site
  • A61B2017/00084—Temperature
• • 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
  • A61F2009/00844—Feedback systems
• • 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
  • A61F2009/00897—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

• the invention relates to a device for ophthalmic laser surgery and an associated method.
• Pulsed laser radiation is used in numerous techniques of treating the human eye.
• the local control of the beam focus of the laser beam in the z-direction (meaning the propagation direction of the laser beam according to the usual notation) always takes place with reference to a known reference point or a known reference surface in the coordinate system of the laser device.
• different reference points or reference surfaces can serve as a reference for the z-control of the beam focus.
• the eye to be treated is pressed against a transparent contact element which, with its eye-facing contact surface, forms a reference surface for the positioning of the beam focus in the z-direction.
• treatment techniques which serve to produce sections (incisions) in the eye tissue by means of focused femtosecond laser radiation frequently make use of such contact elements as the z-reference for the laser focus.
• the cut or the individual photodisruption (the production of cuts in the human eye by means of pulsed femtosecond laser radiation is based regularly on the effect of the so-called laser-induced optical breakthrough to a Photodisruption leads) is located at the desired position in the depth of the eye tissue.
• Laser-produced sections are used, for example, in the case of the so-called Fs-LASIK, in which an anterior cover disc of the cornea known as flap is cut free by femtosecond laser radiation in order subsequently to resemble as in the classical LASIK technique (LASIK: Laser In Sito Keratomi-Ieusis) to flap aside in the hinge area on the remaining corneal tissue flap and ablat Schlud edit the thus exposed tissue by means of UV laser radiation.
• LASIK Laser In Sito Keratomi-Ieusis
• This slice is then removed through an additional cut led out to the ocular surface (the additional incision is made either by means of a scalpel or likewise by means of femtosecond laser radiation).
• Corneal grafting (keratoplasty) or other incisions, for example for corneal ring segments, can also produce corneal incision by means of focused pulsed laser radiation.
• the contact element (applicator) carrying the contact surface is often a disposable article which must be exchanged before each treatment.
• Certain manufacturing tolerances can not be ruled out regularly in the manufacture of the contact elements, even with the greatest precision of manufacture. Therefore, after an exchange of the contact element, the z-position of the eye-facing Kunststoffflädhe - albeit only slightly - be different than in the previously used contact element.
• the smallest possible focal diameter is sought in order to limit the photodisruptive effect locally as closely as possible.
• Modern devices for example, work with focus diameters in the low single-digit pm range.
• the tissue to be treated and the optical system of the laser are usually fixedly coupled to one another by a contact element in order to achieve the required depth of cut with corresponding precision in the z-direction.
• This requires a correspondingly high manufacturing accuracy of the contact element, which, however, can not always be guaranteed.
• the problem arises of a non-precise z-directional cut in the corneal tissue i. the manufacturing tolerances for these contact elements go directly into the inaccuracies for the depth of cut in the tissue.
• the effective depth of cut is in addition to the specified manufacturing tolerances of temperature drifts the dimension of the applicator and the effective focal length of the entire optics dependent, ie the real optical length of the applicator in ⁇ out propagation of treatment laser beam and the focal length of the optics of a laser system vary depending on the temperature range.
• the mentioned drifts can easily add up to 30 ⁇ m in the conventional temperature range of medical devices from 15 ° C to 35 ° C to 30 ⁇ m.
• the desired cutting depth tolerances are ⁇ 5 pm difficult or no longer achievable.
• an apparatus for ophthalmic laser surgery comprising the following components: an optical imaging system for imaging a treatment laser beam on a focal point, a temperature measuring device for measuring a temperature associated with the imaging system and an electronic control device connected to the temperature measuring device is set up to control the focal point adjustment depending on the measured temperature.
• the device may comprise a contact surface for the shaping of an eye to be treated and a radiation source for the provision of the treatment laser beam.
• the imaging system may include optical components for directing the treatment laser beam through the contact surface to the eye.
• the invention enables a control and / or readjustment of, for example, a preset position of the laser beam focus in the z-direction (corresponding to the propagation direction of the treatment laser beam) depending on the measured temperature of the critical components (eg the objective, the beam widening component, etc .) and around the device.
• the presetting of the focus point can be done in different ways.
• the position of the focus in the z-direction can be preset, for example, by knowing the z-position of the contact surface with respect to a given reference point in a fixed coordinate system of the laser-surgical device.
• a patient adapter (applicator) is used whose real optical length in the propagation direction of the treatment laser beam (z-direction) has been produced with high precision, so that the focal point can be preset to the known length.
• Changes in the length of the applicator or changes in the effective focal length of the optical components contained in the device due to the temperature changing around the device can be detected by the temperature measuring device and taken into account accordingly by the control arrangement.
• the effective optical distance (the real optical length) between the eye-facing surface of the applicator (the contact surface) and the surface facing away from the eye (the surface facing the optical components of the device) has already been measured outside the device and has been impressed on the associated applicator via a coding.
• This coding can then by the device, eg automatically or manually, be read and passed on to the control arrangement. Based on the read value, the control arrangement may initially preset the focus point.
• the device preferably has a measuring device for position measurement of the contact surface with respect to the propagation direction of the treatment laser beam.
• the measuring device comprises, for example, a second radiation source providing a measuring beam.
• the optical components are then preferably designed and arranged to also direct the measuring beam through the contact surface to the eye.
• the measuring device may preferably provide position measuring data by means of the measuring beam, which are representative of the measured position of the contact surface at at least one point thereof, and may pass on the determined position measuring data to the control arrangement.
• the electronic control device may preset the focus point depending on the position measurement data.
• the focal point can first be preset in the z-direction, so that manufacturing inaccuracies are reduced or avoided. Based on the measured temperature, the preset focus point can then be adjusted or readjusted.
• the adjustment or readjustment of the preset focus point can take place at predetermined time intervals, for example, by a repeated measurement of the temperature by the temperature measuring device after predetermined periods of time.
• a readjustment can take place when the measured temperature exceeds the previously measured temperature by a predetermined limit.
• a reduction of the predetermined limit value allows a more accurate but more complex readjustment of the focal point.
• the predetermined time intervals and the predetermined limit value are stored in a memory connected to the control arrangement, so that the control arrangement reads these values as required and the temperature measuring device and the readjustment of the Focus point can control accordingly. It is also conceivable that a renewed temperature measurement only takes place when, for example, a user sends a corresponding instruction to the temperature measuring device or components connected thereto.
• the temperature measuring device may include one or more temperature sensors disposed on one or more of the optical components and connected to the electronic control device.
• the optical components preferably form on the one hand a scanning unit for deflecting the treatment laser beam in a plane orthogonal to the beam path (x-y plane) or a 3D scanning unit for three-dimensional deflection of the treatment laser beam and on the other hand focusing optics for focusing the treatment laser beam into the laser beam focus.
• preferably two temperature sensors are respectively arranged on the scanning unit and on the focusing optics.
• one or more than two temperature sensors can also be arranged on the scanning unit and on the focusing optics.
• the optical components comprise at least one controllable optical element.
• the controllable optical element is formed by a position-variable in the propagation direction of the treatment laser beam lens.
• the control arrangement can generate a manipulated variable for readjustment of the preset focal point as a function of the measured temperature.
• the lens for example, can be moved or repositioned mechanically along the optical beam path.
• the control arrangement is preferably configured to change the position of the positionally variable lens by the determined manipulated variable in order to adapt the focus point.
• a controllable liquid lens of variable refractive power With unchanged z-position and otherwise unchanged setting of the focusing lens, a z-displacement of the beam focus can be achieved by moving a longitudinally adjustable lens or by refractive power variation of a liquid lens, thereby adjusting the focus point to the changed temperature. It is understood that for z-adjustment of the beam focus also other components are conceivable, such as a deformable mirror.
• the control arrangement may further comprise or be connected to a memory unit in which the dependency of the focal point on the temperature is stored as a function.
• the temperature dependencies of all in the Device used and all occurring in the device distances can be used to calculate a temperature response of the effective focal length of the optical components from a reference temperature.
• the temperature response is preferably determined separately for the scanning unit and the focusing optics and recorded, but can also be calculated together for these.
• the determined temperature response can be stored as a set of curves in the memory unit and queried as needed by the control arrangement and used to adjust the focus point based on the stored set of curves.
• the control arrangement can also be set up to produce different manipulated variables for the controllable optical element in the z-direction at the regulation of the focal point at several different locations in an x-y plane orthogonal to the z-direction. This makes it possible, for example, individually compensate for different effects of temperature changes on the position of the contact surface in the x-y plane.
• the measuring device is preferably a coherence-optical interferometric measuring device and has an optical interferometer for this purpose.
• the contact surface will often be part of a replaceable disposable component, such as a disposable applicator. However, it should be emphasized that the invention does not assume a disposable character of the element carrying the contact surface. The invention is equally applicable in embodiments with permanently installed or at least reusable contact surface.
• the contact surface is preferably formed by a transparent applanation plate or a transparent contact glass. Applanation plates have at least on their facing plate side a flat applanation surface with which a leveling of the front of the eye is achieved. The use of applanation plates for referencing the eye to be treated is regularly favorable from the viewpoint of a high beam quality of the laser radiation.
• contact element a contact lens with a typically concave or convex-shaped eye-facing lens surface.
• the advantage of such contact glasses is z. B. a lesser increase in intraocular pressure when pressed against the eye.
• the contact surface is formed in a preferred embodiment of a transparent contact element, which is part of a patient with a focusing lens of the device, in particular interchangeable coupled patient adapter.
• the invention further provides a method for controlling a focal point of a treatment laser beam for ophthalmic laser surgery, comprising the steps:
• the method may further comprise the steps of forming a forming abutment contact between an eye and a contact surface and directing the treatment laser beam through the contact surface to the eye.
• position measurement data representative of a measured position of the contact surface at at least one location thereof relative to the propagation direction of the treatment laser beam may be determined or read as described above. Regardless of whether the position measurement data has been determined or read out, the focal point can be preset depending on the position measurement data and subsequently readjusted based on the measured temperature.
• FIG. 1 is a highly schematic representation of a first embodiment of a device for ophthalmic laser surgery.
• FIG. 2 is a highly schematic representation of a second embodiment of a device for ophthalmic laser surgery.
• the laser surgical device according to both embodiments is indicated generally at 10.
• the laser surgical device 10 has a femtosecond laser (Fs laser) 12, which emits pulsed laser radiation with pulse durations in the range of femtoseconds.
• the laser radiation propagates along an optical beam path 14 and finally reaches an eye 16 to be treated.
• Various components for guiding and shaping the laser radiation are arranged in the beam path 14.
• these components comprise a focusing objective 18 (for example an F-theta objective) and a scanner 20 connected upstream of the objective 18, by means of which the laser radiation provided by the laser 12 can be deflected in a plane orthogonal to the beam path 14 (xy plane) ,
• a drawn coordinate system illustrates this plane as well as a z-axis defined by the direction of the beam path 14.
• the scanner 20 is constructed, for example, in a manner known per se from a pair of galvanometrically controlled deflection mirrors which are each responsible for the beam deflection in the direction of one of the axes spanning the x-y plane.
• a central control unit 22 controls the scanner 20 in accordance with a control program stored in a memory 24 which implements a cutting profile to be generated in the eye 16 (represented by a three-dimensional pattern of sampling points at which photodisruption is to be effected).
• the mentioned components for guiding and shaping the laser radiation include at least one controllable optical element 26 for z-adjustment of the beam focus of the laser radiation.
• this optical element is formed by a lens.
• a suitable actuator 28 is used, which in turn is controlled by the control unit 22.
• the lens 26 can be moved mechanically along the optical beam path 14.
• a controllable liquid lens of variable refractive power it is conceivable to use a controllable liquid lens of variable refractive power. turn. With unchanged z-position and otherwise unchanged setting of the focusing lens 18 can be achieved by moving a longitudinally adjustable lens or by refractive power variation of a liquid lens, a z-displacement of the beam focus.
• the lens 26 can also be part of the scanner 20 and the scanner 20 formed thereby can be arranged both before and after the semitransparent deflection mirror 40. The case where the lens is part of the scanner 20 and the scanner 26 including the lens 26 is disposed in front of the reflecting mirror 42 will be explained later with reference to FIG.
• the focusing objective 18 is coupled to a patient adapter 30, which serves to establish a mechanical coupling between the eye 16 and the focusing objective 18.
• a patient adapter 30 which serves to establish a mechanical coupling between the eye 16 and the focusing objective 18.
• suction ring is placed on the eye and fixed there by suction.
• the suction ring and the patient adapter 30 form a defined mechanical interface, which allows a coupling of the patient adapter 30 to the suction ring.
• the patient adapter 30 serves as a support for a transparent contact element 32, which in the example shown is designed as a plane-parallel applanation plate.
• the patient adapter 30 comprises, for example, a cone sleeve body, on whose narrower (in the drawing lower) sleeve end the applanation plate 32 is arranged.
• the wider (in the drawing upper) sleeve end of the patient adapter 30 is attached to the focusing lens 18 and there has suitable formations that allow an optionally releasable fixation of the patient adapter 30 to the focusing lens 18.
• the applanation plate 32 is a hygienically critical article Therefore, it is expedient to replace it after each treatment.
• the applanation plate 32 can be exchangeably attached to the patient adapter 30.
• the patient adapter 30 together with the applanation plate 32 form a disposable unit, to which the applanation plate 32 can be permanently connected to the patient adapter 30.
• the eye-facing underside of the applanation plate 32 forms a flat contact surface 34 against which the eye 16 is pressed in preparation for the treatment. This causes a planarization of the anterior surface of the eye with simultaneous deformation of the cornea of the eye 16, designated 36.
• the laser surgical device 10 contains a coherence-optical interferometric measuring device 38, for example an OLCR measuring device (OLCR: Optical Low Coherence Reflectrometry), which emits a measuring beam, which is coupled into the beam path 14 by means of an immovably arranged, semitransparent deflecting mirror 40 which also the treatment laser radiation of the laser 12 is running.
• the measuring device 38 brings the generated measuring beam into interference with a reflection beam returning from the eye 16. From the interference measurement data obtained in this regard, the z-position of the contact surface 34 within the coordinate system of the laser-surgical device can be determined. Therefore, the interference measurement data can also be referred to as position measurement data.
• the control unit 22 receives the interference measurement data from the measuring device 38 and calculates therefrom the z-position of that point of the contact surface 34 at which the measuring beam impinged or through which the measuring beam passed.
• the measuring beam emitted by the measuring device 38 passes through the scanner 20. This makes it possible to use the deflection function of the scanner 20 also for the measuring beam.
• the scanner module 20 could also include a second separate scanner for the OLCR alone, which works much faster with smaller mirrors.
• control unit 22 takes into account the thus determined actual z-position of the contact surface 34 in the z-control of the beam focus, such that the incision is actually generated at the intended position in the depth of the cornea 36.
• the evaluation and control unit 22 references the z-position of the beam focus to be set to the measured z position of the contact surface 34.
• the jersey surgical device 10 has four temperature sensors 50, 52, 54, 56, two of which are disposed on the scanner 20 and two on the focusing lens 18.
• the temperature sensors measure the real temperature at their respective positions and relay the measured temperature values to the control unit 22.
• the transmission of the temperature values to the control unit 22 may be wireless or wired, i. the temperature sensors 50, 52, 54, 56 may be in wireless or wired communication with the control unit 22.
• the scanner 20 and thus the temperature sensors 50, 52 arranged on the scanner 20 are connected by wire to the control unit 22, while the temperature sensors 54, 56 arranged on the focusing lens 18 are wirelessly connected to the control unit 22 to pass their temperature readings to the control unit 22 for further processing.
• a temperature response of the effective focal length is deposited as a set of curves both for the scanner 20 and for the focusing lens 18.
• the control unit evaluates the corresponding function in the presence of a new temperature measured value and generates a corresponding manipulated variable for readjustment of the preset z-position of the lens 26. If one or both of the temperature sensors 50, 52 mounted on the scanner 20 determines a temperature value (during the measurement of two temperature values by the two temperature sensors 50, 52, an average temperature value formed from the two values is used), the temperature sensor transmits the measured temperature value to the control unit 22.
• the latter searches the memory 20 for the associated temperature response for the scanner 20, generates a manipulated variable therefrom and transmits it to the actuator 28, which shifts the lens 26 in the z direction in accordance with the manipulated variable.
• the preset position of the beam focus is readjusted in such a way that changes in the real optical length of the patient adapter and / or the effective focal length of the laser surgical device 10 that occur due to fluctuations in the real temperature are taken into account and compensated for.
• the scanner 20 comprises the lens 26, which is displaceable in the direction of propagation of the treatment laser beam, and is arranged in front of the deflection mirror 42 in the propagation direction of the laser radiation.
• the scanner 20 is a 3D scanner having three-dimensional scanning properties, so that the laser radiation can be deflected in any direction (x, y, z) from the 3D scanner 20.

Landscapes

• Health & Medical Sciences (AREA)
• Ophthalmology & Optometry (AREA)
• Heart & Thoracic Surgery (AREA)
• Vascular Medicine (AREA)
• Veterinary Medicine (AREA)
• Surgery (AREA)
• Engineering & Computer Science (AREA)
• Biomedical Technology (AREA)
• Public Health (AREA)
• Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
• Life Sciences & Earth Sciences (AREA)
• Animal Behavior & Ethology (AREA)
• General Health & Medical Sciences (AREA)
• Physics & Mathematics (AREA)
• Optics & Photonics (AREA)
• Transplantation (AREA)
• Laser Surgery Devices (AREA)
• Laser Beam Processing (AREA)

Priority Applications (11)

Applications Claiming Priority (1)

Publications (1)

Family

ID=42338384

Family Applications (1)

Country Status (11)

Cited By (4)

Families Citing this family (5)

Citations (4)

Family Cites Families (11)

• 2009
  • 2009-12-07 WO PCT/EP2009/008747 patent/WO2011069516A1/de active Application Filing
  • 2009-12-07 CA CA2772138A patent/CA2772138C/en not_active Expired - Fee Related
  • 2009-12-07 CN CN200980161176.2A patent/CN102481205B/zh not_active Expired - Fee Related
  • 2009-12-07 KR KR1020127012980A patent/KR101441100B1/ko active IP Right Grant
  • 2009-12-07 EP EP09768502.8A patent/EP2445461B1/de active Active
  • 2009-12-07 BR BR112012006400A patent/BR112012006400A2/pt active Search and Examination
  • 2009-12-07 MX MX2012003189A patent/MX2012003189A/es active IP Right Grant
  • 2009-12-07 ES ES09768502.8T patent/ES2485910T3/es active Active
  • 2009-12-07 JP JP2012542363A patent/JP5785182B2/ja active Active
  • 2009-12-07 RU RU2012124965/14A patent/RU2526975C2/ru not_active IP Right Cessation
• 2010
  • 2010-12-01 TW TW099141692A patent/TW201127361A/zh unknown

Patent Citations (4)

Also Published As

Similar Documents

Legal Events