Patent Publication Number: US-11642245-B2

Title: Apparatus for working on eye tissue by means of a pulsed laser beam

Description:
CROSS REFERENCE TO RELATED APPLICATIONS 
     This application is a continuation application of U.S. application Ser. No. 16/009,701, filed Jun. 15, 2018, now U.S. Pat. No. 10,918,523, issued Feb. 16, 2021, which claims priority to and the benefit of European Patent Application No. 17020300.4 filed on Jul. 13, 2017. The above-identified applications are incorporated by reference herein in their entireties. 
    
    
     FIELD OF TECHNOLOGY 
     The present disclosure relates to an ophthalmological apparatus for working on eye tissue by means of a pulsed laser beam. In particular, the present disclosure relates to an ophthalmological apparatus with a laser source for producing a pulsed laser beam, a focusing optical unit for focusing the pulsed laser beam into the eye tissue and a scanner system for guiding the pulsed laser beam onto a work target point in the eye tissue. 
     BACKGROUND 
     For the purposes of working on eye tissue by means of a laser beam, a work region is scanned by laser pulses by virtue of the pulsed laser beam being deflected in one or two scan directions by means of suitable scanner systems (deflection apparatuses). In general, movable mirrors are used to deflect the light beams and/or the laser pulses, for example femtosecond laser pulses, said movable mirrors being pivotable about one or two scan axes, for example by way of galvano scanners, piezo scanners, polygon scanners or resonance scanners. 
     U.S. Pat. No. 7,621,637 describes an apparatus for working on eye tissue, said apparatus having a base station with a laser source for producing laser pulses and a scanner, arranged in the base station, with movable deflection mirrors for deflecting the laser pulses in a scan direction. The deflected laser pulses are transferred via an optical relay system from the base station to an application head, the latter passing over a work region according to a scan pattern by means of a mechanically moved projection optical unit. 
     In the application head, the deflection in the scan direction, which is much faster in comparison with the mechanical movement, is overlaid onto the mechanical movement of the projection optical unit and consequently onto the scan pattern thereof. A fast scanner system in the base station facilitates a fine movement of the laser pulses (micro-scan), which is overlaid on the scan pattern of the movable projection optical unit that covers a large work region, for example the entire eye. 
     Such known systems facilitate working on simple scan patterns, for example cutting a tissue flap, which, as a rule, is embodied as a large area piece with a simple edge geometry. In applications in which tissue cuts should not only be carried out in the work area that is aligned substantially horizontally on a common focal area but also be carried out with a vertical cut component with different focal heights, e.g. cuts that extend at an angle to the horizontal or vertical cuts, the vertical displacement of the projection optical unit or of a zoom system for a vertical change in the focus, and hence in the cut height, was found to be too slow to carry out cuts with a vertical component, i.e. with a modifiable focal depth during cutting, with a speed that is comparable to the cut speeds in the horizontal work area. 
     US 2016/0089270 describes a system and a method for cutting lenticules in the eye tissue. According to US 2016/0089270, straight-lined fast scan lines are overlaid to this end on slower work lines that are traced out along meridians of the lenticule. Cuts that deviate in terms of their form from the desired surface curvature of the lenticule and consequently cause errors arise on account of the straight-line property of the fast scan lines. Moreover, a vertical focal displacement of the order and to the extent of the thickness of the lenticule to be cut is required in order to trace out the work lines along the meridians, in each case over the distance of a lenticule width; firstly, this is connected to corresponding outlay and costs for displaceable optical units and movable lenses that are configured to this end and, secondly, this is connected to losses in the work speed accompanying this. Moreover, on account of their fixed horizontal alignment, the fast scan lines do not allow best possible matching of cuts to lenticule surfaces, particularly not if these deviate from the spherical form. 
     SUMMARY 
     It is an advantage of the present disclosure to propose an apparatus for working on eye tissue by means of a pulsed laser beam, which does not have at least some of the disadvantages of the prior art. 
     According to the present disclosure, these advantages are achieved by the features of the independent claims. Moreover, further advantages emerge from the dependent claims and the description. 
     In one example, an ophthalmological apparatus for working on eye tissue, in particular for cutting a lenticule in the eye tissue, comprises a laser source that is configured to produce a pulsed laser beam; a focusing optical unit that is configured to focus the pulsed laser beam into the eye tissue; a scanner system, comprising a first scanner module and a second scanner module, for deflecting the pulsed laser beam onto work target points in the eye tissue; and a circuit for controlling the ophthalmological apparatus; and the aforementioned advantages are at least partially achieved by virtue of the circuit being configured to control the second scanner module in such a way that the second scanner module guides the pulsed laser beam in a feed direction onto work target points along a work line that extends along an outer face of a lenticule to be cut in the eye tissue, transversely to the meridians of the lenticule. The first scanner module is configured to guide the pulsed laser beam onto work target points along a scan line that extends across the work line at an alignment angle in a horizontal work plane, with a substantially higher scanning speed in comparison with the scanning speed of the second scanner module in the feed direction. The ophthalmological apparatus comprises a z-modulator that is configured to tilt the scan line out of the work plane depending on a specific work target point of the second scanner module on the work line such that the scan line runs substantially along the outer face of the lenticule. As a result of this tilt of the scanning line (that is scanned comparatively faster) depending on the current work target point of the work line (that is scanned comparatively slower), it is possible, in the eye tissue, to cut lenticules with a plurality of cut trajectories lying next to one another that are tilted out of the horizontal work plane without substantial deviations from the surface curvature of the lenticule to be cut being produced in the process. Particularly in comparison with solutions that have fixed horizontally aligned scan lines that do not permit ideal cut matching to the surface curvatures of lenticules, the dynamic change of the scan line tilt facilitates more flexible and precise cut matching to lenticule surfaces with a locally varying surface curvature. Depending on the selected form of the work line, it is moreover possible to cut the lenticules in the eye tissue without this requiring focal displacements, vertical thereto, of the order and to the extent of the entire depth of the vertical cut component to be performed, i.e. the thickness of the lenticule to be cut, by way of displacements of the projection optical unit or movements of lenses of a zoom system with a speed with which the second scanner module traces over a distance of the work line that corresponds to the lateral extent of the lenticule to be cut. 
     In one illustrative example variant, the ophthalmological apparatus comprises a rotator that is configured to rotate a fast scan plane defined by the scan line and the pulsed laser beam about an optical transmission axis in such a way that the alignment angle of the scan line is modified in relation to the work line. 
     In a further illustrative example variant, the circuit is configured to control the rotator depending on the specific work target point of the second scanner module on the work line such that the alignment angle of the scan line relative to the work line is set depending on the specific work target point of the second scanner module on the work line. 
     In one illustrative example variant, the ophthalmological apparatus comprises a scan length modulator that is configured to modify a length of the scan line. The circuit is configured to control the scan length modulator depending on the specific work target point of the second scanner module on the work line such that the length of the scan line is set depending on the specific work target point of the second scanner module on the work line. 
     In a further illustrative example variant, the circuit is configured to control the second scanner module in such a way that the second scanner module guides the pulsed laser beam onto work target points in the work plane along a circular or elliptical work line that extends along the outer face of the lenticule. 
     In one illustrative example variant, the circuit is configured to control the second scanner module in such a way that the second scanner module guides the pulsed laser beam in succession along a plurality of circular or elliptical work lines that are arranged in work planes lying above one another and that extend along the outer face of the lenticule. 
     In a further illustrative example variant, the circuit is configured to control the second scanner module in such a way that the second scanner module guides the pulsed laser beam onto work target points along a spiral work line that extends along the outer face of the lenticule. 
     In one illustrative example variant, the circuit is configured to control the second scanner module in such a way that the second scanner module guides the pulsed laser beam onto work target points along a work line that extends along the outer face of the lenticule in the form of a circular arc segment, a spiral arc segment or a curved line segment. 
     In a further illustrative example variant, the circuit is configured to control the second scanner module in such a way that the second scanner module guides the pulsed laser beam onto work target points along a plurality of spiral work lines, said work lines extending in a spiral arm shape in the direction of a centre of the outer face proceeding from a periphery of the outer face of the lenticule in a first step, and extending in a spiral arm shape to the periphery of the outer face of the lenticule proceeding from the centre in a second step. 
     In one illustrative example variant, the circuit is configured to control the second scanner module in such a way that the second scanner module guides the pulsed laser beam onto work target points along a plurality of spiral work lines, said work lines extending in a spiral arm shape in the direction of a centre of the outer face proceeding from a periphery of the outer face of the lenticule and ending at a specific distance from the centre in a first step, and extending in a spiral arm shape to the periphery of the outer face of the lenticule proceeding from the specific distance from the centre in a second step, or conversely, extending in a spiral arm shape to the periphery of the outer face of the lenticule proceeding from the specific distance from the centre in a first step and extending in a spiral arm shape in the direction of the centre of the outer face from the periphery of the outer face of the lenticule. 
     In a further illustrative example variant, the z-modulator is configured to bend the scan line in relation to the work plane. The circuit is configured to control the z-modulator depending on the specific work target point of the second scanner module on the work line in such a way that the z-modulator bends the scan line depending on the specific work target point of the second scanner module on the work line for the purposes of adaptation to the outer face of the lenticule. 
     In one illustrative example variant, the ophthalmological apparatus comprises a rotator that is configured to rotate a fast scan plane defined by the scan line and the pulsed laser beam about an optical transmission axis in order to modify the alignment angle of the scan line in relation to the work line. The z-modulator is configured to bend the scan line in relation to the work plane. The ophthalmological apparatus comprises a scan length modulator that is configured to modify a length of the scan line. The circuit is configured, depending on the specific work target point of the second scanner module on the work line, to control the rotator to set the alignment angle of the scan line in relation to the work line, to control the z-modulator to bend the scan line in relation to the work plane and to control the scan length modulator to set the length of the scan line in such a way that the outer face of the lenticule is cut in a predetermined free-form for the purposes of correcting a higher-order aberration. 
     In a further illustrative example variant, the ophthalmological apparatus comprises a rotator that is configured to rotate a fast scan plane defined by the scan line and the pulsed laser beam about an optical transmission axis in order to modify the alignment angle of the scan line in relation to the work line. The ophthalmological apparatus comprises a scan length modulator that is configured to modify a length of the scan line. The circuit is configured, depending on the specific work target point of the second scanner module on the work line, to control the rotator to set the alignment angle of the scan line in relation to the work line, to control the z-modulator to tilt the scan line in relation to the work plane and to control the scan length modulator to set the length of the scan line in such a way that the outer face of the lenticule is cut in a predetermined free-form for the purposes of correcting a higher-order aberration. 
     In one example, the ophthalmological apparatus for working on eye tissue comprises a laser source that is configured to produce a pulsed laser beam; a focusing optical unit that is configured to focus the pulsed laser beam into the eye tissue; and a scanner system that is configured to guide the pulsed laser beam onto work target points in the eye tissue; and the aforementioned advantages are at least partly achieved by virtue of the circuit being configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points in an area to be cut in a cornea, in work trajectories that extend next to one another, in order, initially, to produce cut trajectories, separated by remaining tissue bridges, of a tissue cut to be undertaken in the area and in order, thereafter, to guide the pulsed laser beam onto work target points in the remaining tissue bridges between the cut trajectories in the area in order to complete the tissue cut. Cutting cut trajectories that are separated by tissue bridges in each case facilitates the cut of a new cut trajectory without the latter being impaired by deformations that are caused by the formation of gas in an already cut, directly adjacent cut trajectory. 
     In one illustrative example variant, the ophthalmological apparatus comprises a measurement system that is configured to optically capture structures in the eye tissue. The circuit is configured to control the measurement system in such a way that the measurement system captures the produced cut trajectories and positions the work target points in the remaining tissue bridges on the basis of the captured cut trajectories. In one illustrative example variant, the measurement system is embodied as an interferometric measurement system. Capturing cut trajectories already cut and working on remaining tissue bridges taking account of the cut trajectories already cut facilitates a flexible adaptation to the actual form of performed cut trajectories and thereby facilitates an avoidance of, or at least reduction in, overlapping cut trajectories over extended regions. 
     In a further illustrative example variant, the circuit is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam with overlapping laser pulse spots onto successive work target points. 
     In one illustrative example variant, the circuit is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points in the work trajectories extending next to one another into the remaining tissue bridges. 
     In a further illustrative example variant, the circuit is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam in the remaining tissue bridges onto work target points in work trajectories which have a width going beyond the tissue bridges. 
     In one illustrative example variant, the circuit is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points in work trajectories that extend parallel next to one another. 
     In a further illustrative example variant, the circuit is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points in work trajectories that extend next to one another, said work trajectories having a spiral, circular or elliptical form. 
     In one illustrative example variant, the circuit is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam in a feed direction onto work target points along a work line extending in the work trajectories. The scanner system is configured to guide the pulsed laser beam along a scan line, extending across the work line, within the work trajectories with a substantially higher scan speed in comparison with the scan speed in the feed direction. 
     In a further illustrative example variant, the circuit is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points on an outer side of a lenticule to be cut in a cornea, in the work trajectories extending next to one another, in order to produce the cut trajectories of the tissue cut to be undertaken at the outer face of the lenticule, said cut trajectories being separated by remaining tissue bridges, and thereafter guides the pulsed laser beam onto work target points in the remaining tissue bridges between the cut trajectories on the outer face of the lenticule in order to complete the tissue cut. 
     In one illustrative example variant, the circuit is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points onto the lower outer face of the lenticule to be cut, facing away from an outer corneal surface, in order to produce the cut trajectories, separated by remaining tissue bridges, on the lower outer face of the lenticule to be cut and that the scanner system thereupon guides the pulsed laser beam onto work target points on an upper outer face of the lenticule be cut, facing the outer corneal surface, in work trajectories extending next to one another, in order to produce cut trajectories, separated by remaining tissue bridges, of an upper tissue cut to be undertaken on the upper outer face of the lenticule before the scanner system guides the pulsed laser beam onto the work target points into the remaining tissue bridges on the lower outer face of the lenticule in order to complete the lower tissue cut; and that the scanner system thereupon guides the pulsed laser beam onto work target points into the remaining tissue bridges on the upper outer face of the lenticule in order to complete the upper tissue cut. 
     In a further illustrative example variant, the ophthalmological apparatus comprises a measurement system that is configured to optically capture structures in the eye tissue. The circuit is configured to control the measurement system in such a way that the measurement system captures the produced cut trajectories of the lower tissue cut to be undertaken and positions, in respect of the captured cut trajectories of the lower tissue cut, the work trajectories of the upper tissue cut to be undertaken. In one illustrative example variant, the measurement system is embodied as an interferometric measurement system. 
     In a further illustrative example variant, the circuit is configured to determine the work trajectories of the upper tissue cut to be undertaken with a smaller trajectory width in respect of the captured cut trajectories of the lower tissue cut. 
     In one illustrative example variant, the circuit is configured to position the work trajectories for completing the lower tissue cut in relation to the captured cut trajectories of the lower tissue cut. 
     In one example, the ophthalmological apparatus for working on eye tissue comprises a laser source that is configured to produce a pulsed laser beam; a focusing optical unit that is configured to focus the pulsed laser beam into the eye tissue; and a scanner system that is configured to guide the pulsed laser beam onto work target points in the eye tissue; a measurement system that is configured to optically capture structures in the eye tissue; and a circuit that is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points on a first outer face of a lenticule to be cut in the eye tissue in order to produce a first tissue cut for cutting the lenticule; and the aforementioned advantages are at least partly achieved by virtue of the circuit moreover being configured to control the measurement system in such a way that the measurement system captures the first outer face of the lenticule that is produced by the first tissue cut and to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points on a second outer face, positioned in relation to the captured first outer face of the lenticule, of the lenticule to be cut in order to produce a second tissue cut, positioned in relation to the captured first outer face of the lenticule, for cutting the lenticule. In one illustrative example variant, the measurement system is embodied as an interferometric measurement system. Capturing a tissue cut on a first outer face of a lenticule to be cut and, dependent thereon, positioning and carrying out a tissue cut on a second outer face of the lenticule facilitates a flexible and precise adaptation of form and orientation of the tissue cut to be carried out or of the second outer face in relation to the actual orientation and form of the tissue cut already carried out and thereby brings about an improvement in form and size of the lenticule, in particular in the thickness thereof, and in the desired refractive correction of the eye achievable therewith. In one illustrative example variant, the circuit is configured to position the second outer face of the lenticule to be cut, with a predetermined centre thickness of the lenticule to be cut, in relation to the captured first outer face. 
     In a further illustrative example variant, the circuit is configured to position the second outer face of the lenticule to be cut, with a predetermined thickness profile of the lenticule to be cut, in relation to the captured first outer face. 
     In one illustrative example variant, the circuit is configured to control the measurement system in such a way that the measurement system captures deformations of the first outer face caused by gas bubbles produced during the first tissue cut and positions the second outer face of the lenticule to be cut taking account of the captured deformations in respect of the captured first outer face. 
     In a further illustrative example variant, the circuit is configured to determine the first outer face of the lenticule to be cut as a lower side of the lenticule to be cut facing away from an outer corneal surface and to determine the second outer face of the lenticule to be cut as an upper side of the lenticule to be cut facing the outer corneal surface. 
     In an illustrative example variant, the circuit is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points in work trajectories extending next to one another on the first outer face of the lenticule to be cut in order to produce cut trajectories of the first tissue cut extending next to one another; and to control the measurement system in such a way that the measurement system captures the cut trajectories extending next to one another and positions the second outer face of the lenticule to be cut in relation to the captured cut trajectories extending next to one another. 
     In a further illustrative example variant, the circuit is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points in work trajectories extending next to one another on the first outer face of the lenticule to be cut in order to produce cut trajectories of the first tissue cut that extend next to one another and that are separated by remaining tissue bridges; to control the measurement system in such a way that the measurement system captures the cut trajectories; and to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points in the remaining tissue bridges, determined on the basis of the captured cut trajectories, on the first outer face in order to produce the first tissue cut. 
     In one illustrative example variant, the circuit is configured to control the scanner system in such a way that the scanner system guides the pulsed laser beam onto work target points in work trajectories that extend on the outer face of the lenticule and that have a configuration that is straight lined, that extends along circles, that is concentrically circular, that is concentrically elliptical, that is spiral-shaped or that is spiral-arm-shaped. 
     In a further illustrative example variant, the circuit is configured to control a second scanner module of the scanner system in such a way that the second scanner module guides the pulsed laser beam onto work target points in a feed direction along a work line that extends on the first and/or second outer face of the lenticule to be cut; that the scanner system comprises a first scanner module that is configured to guide the pulsed laser beam along a scan line extending across the work line at an alignment angle in the horizontal work plane, with a substantially higher scan speed in comparison with the scan speed of the second scanner module in the feed direction; and that the scanner system comprises a z-modulator that is configured to tilt the scan line out of the work plane depending on a specific work target point of the second scanner module on the work line in such a way that the scan line extends substantially along the outer face of the lenticule. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       An illustrative example of the present disclosure is described below on the basis of an example. The example of the illustrative example is illustrated by the figures attached below: 
         FIG.  1    shows a block diagram that schematically illustrates an ophthalmological apparatus for working on eye tissue with a pulsed laser beam, said apparatus comprising a scanner system for scanning the eye tissue with the pulsed laser beam at work target points in the eye tissue. 
         FIG.  2    shows a block diagram of the ophthalmological apparatus, which illustrates a plurality of modules of the scanner system that contribute to guiding the pulsed laser beam along a scan line extending across a work line. 
         FIG.  2   a    shows a schematic plan view of an eye tissue region, which illustrates a work line in the feed direction and a scan line extending across the work line. 
         FIG.  2   b    shows a schematic cross-sectional view of an eye tissue region, which illustrates a work line that extends in a work plane extending perpendicular to the plane of the drawing, and a scan line that is tilted out of the work plane. 
         FIG.  3    shows a schematic cross section of a portion of the beam path in a divergence modulator with at least one displaceable lens and illustrates the divergence of the laser beam that is modified by displacing the lens. 
         FIG.  4    shows a schematic cross-sectional view of an eye tissue region with a lenticule cut in the cornea and a portion thereof reproduced in a magnified manner. 
         FIG.  5    shows a schematic plan view of a lenticule in the eye tissue, which is cut by a plurality of concentric circular work lines that extend across meridians of the lenticule and by scan lines extending thereacross. 
         FIG.  6    shows a schematic plan view of a lenticule in the eye tissue, which is cut by a plurality of concentric elliptical work lines that extend across meridians of the lenticule and by scan lines extending thereacross. 
         FIG.  7    shows a schematic plan view of a lenticule in the eye tissue, which is cut by a spiral work line that extends across meridians of the lenticule and by scan lines extending thereacross. 
         FIG.  8    shows a schematic plan view of a lenticule in the eye tissue, which is cut by spiral-arm-shaped work lines that extend across meridians of the lenticule and by scan lines extending thereacross. 
         FIG.  9    shows a schematic plan view of a lenticule in the eye tissue, which is cut by a plurality of concentric work lines that extend across meridians of the lenticule and by scan lines extending thereacross. 
         FIG.  10    shows a schematic plan view of a lenticule in the eye tissue, which is cut by a plurality of concentric curved work lines that extend across meridians of the lenticule and by scan lines extending thereacross. 
         FIG.  11    shows a schematic cross-sectional view of a lenticule that is cut into the eye tissue of the cornea in the applanated state of the cornea for the purposes of correcting hyperopia. 
         FIG.  12    shows a schematic plan view of a lenticule in the eye tissue, which is cut by spiral-arm-shaped, elliptical work lines that extend across meridians of the lenticule and by scan lines extending thereacross. 
         FIG.  13    shows a schematic plan view of a lenticule in the eye tissue, which is cut by a plurality of parallel work lines that extend across meridians of the lenticule and by scan lines extending thereacross. 
         FIG.  14    shows a schematic cross-sectional view of a lenticule, which is cut by a plurality of parallel work lines that extend across meridians of the lenticule and by scan lines extending thereacross, wherein the scan lines of work lines extending next to one another are tilted differently in relation to a work plane that extends perpendicular to the plane of the drawing. 
         FIG.  15    shows a schematic view of cut trajectories of a lenticule, extending next to one another, which are separated by remaining tissue bridges in the eye tissue, which are cut by a spiral elliptical work line and by scan lines extending thereacross. 
         FIG.  16    shows a schematic plan view of overlapping laser pulse spots of a pulsed laser beam along a scan line. 
         FIG.  17    shows a flowchart that illustrates carrying out and producing an areal cut in the eye tissue. 
         FIG.  18    shows a flowchart that illustrates carrying out the cut and producing a lenticule in the eye tissue. 
     
    
    
     DETAILED DESCRIPTION 
     In  FIGS.  1  and  2   , the reference sign  1  in each case relates to an ophthalmological apparatus for working on eye tissue  20 , for example the cornea or any other tissue of an eye  2 , by means of laser pulses. 
     As illustrated schematically in  FIGS.  1  and  2   , the ophthalmological apparatus  1  comprises a scanner system  100  for guiding a pulsed laser beam L, supplied by a laser source  11 , via a focusing optical unit  16  onto work target points F in the eye tissue  20 , and a measurement system  17  for optically capturing structures in the eye tissue  20 . The measurement system  17  is embodied as an imaging measurement system, in particular as an interferometric measurement system. 
     The focusing optical unit  16  is configured for focused projection of the pulsed laser beam L and/or the laser pulses for point-by-point disintegration of tissue in a focus F at a work target point in the interior of the eye tissue  20 . In  FIGS.  1  and  2   , the laser beam L that has been focused by the focusing optical unit  16  is denoted by the reference sign L*. 
     By way of example, the focusing optical unit  16  is installed in an application head  160 , which can be placed onto the eye  2 . The application head  160  is preferably placed onto the eye  2  by way of an at least partly light-transparent contact body or a fluid chamber and it is fastened to the eye  2  by means of a vacuum-controlled suction ring, for example, with the contact body and the suction ring being connected to the application head  160  in a fixed or removable manner. In one illustrative example variant, the focusing optical unit  16  comprises a focus adjustment device for setting the focal depth, for example one or more movable lenses, in the focusing optical unit  16  or upstream of the focusing optical unit  16 , or a drive for moving the entire focusing optical unit  16 . 
     In particular, the laser source  11  comprises a femtosecond laser for producing femtosecond laser pulses, which have pulse widths of typically 10 fs to 1000 fs (1 fs=10 15  s). The laser source  11  is arranged in a separate housing or in a housing shared with the focusing optical unit  16 . 
     It should be noted here that the reference sign L denotes, in general, the pulsed laser beam L and/or the laser pulses thereof in the beam path from the laser source  11  to the focus F, but that, depending on the context, further reference signs are also used to denote the pulsed laser beam L and/or the laser pulses thereof at a specific point in the beam path and/or in the scanner system  100 . 
     It is clear from  FIGS.  1  and  2    that the scanner system  100  comprises a plurality of optical functional modules, a first scanner module  12  (fast-scan module), a scan length modulator  18 , a z-modulator  13  and/or  13 ′, a rotator  14  and a second scanner module  15  (slow-scan module). A person skilled in the art will understand that it is possible to dispense with the scan length modulator  18 , the z-modulator  13 ,  13 ′ and/or the rotator  14  depending on the functions to be carried out by the ophthalmological apparatus  1 , which functions will be described herein below. The first scanner module  12  in the ophthalmological apparatus  1  is also optional. 
     As illustrated schematically in  FIGS.  1  and  2   , the ophthalmological apparatus  1  comprises a circuit  10  for controlling the laser source  11 , the optical functional modules of the scanner system  100 , the focusing optical unit  16  and the measurement system  17 . The circuit  10  realizes a programmable control apparatus and comprises e.g. one or more processors with program and data memory and programmed software modules for controlling the processors, and/or other programmable circuits or logic units such as ASICs (application specific integrated circuits). 
     The scanner module  15  (slow-scan module) disposed upstream of the focusing optical unit  16  is configured to scan the eye tissue with the pulsed laser beam L and/or the laser pulses in an x/y-work plane along a work line s, as illustrated in an exemplary manner in the plan view A of  FIG.  2   a   . The scanner module  15  is embodied as a mechanical scanner that drives the focusing optical unit  16  over a work area along the work line s by means of one or more movement drivers such that the focus F is guided along the work line s in the x/y-work plane, or the scanner module  15  has a beam-deflecting illustrative example and comprises one or two deflection mirrors, each movable about one or two axes, for deflecting the pulsed laser beam L and/or the laser pulses in the x/y-work plane along the work line s. The beam-deflecting scanner module  15  is embodied as a freely addressable scanner and comprises e.g. a galvano scanner or a piezo-driven scanner. 
     The scanner module  12  (fast-scan module) disposed upstream of the scanner module  15  is configured to scan the eye tissue with the pulsed laser beam L and/or the laser pulses along a scan line f that is overlaid on the work line s, as illustrated in an exemplary manner in the plan view A of  FIG.  2   a   . The two scanner systems  12  and  15  are configured and coupled in such a way that the scan movement extending along the scan line f is overlaid on the work line s of the scanner module  15 . The scan line f extends across the work line s at an alignment angle ϕ′. The alignment angle ϕ′ between the scan line f and the work line s is adjustable by way of the rotator  14 . The scanner module  12  comprises one or more movable deflection mirrors, for example a rotating polygon mirror (polygon scanner), one or more resonant mirrors (resonant scanner) or oscillating mirrors (oscillating scanner), which are e.g. piezo-driven (piezo-scanner), or MEM (micro-electromechanical) scanners, or the scanner module  12  comprises an AOM (acousto-optic modulator) scanner or an EOM (electro-optic modulator) scanner. The scanner module  12  has a higher, e.g. multiply higher, scan speed than the downstream scanner module  15 . Accordingly, the scanner module  12  can also be referred to as fast-scan module, which produces the deflected laser beam Lf, and the scanner module  15  can be referred to as slow-scan module, which produces the deflected laser beam Ls. 
     As illustrated in  FIG.  16   , in one variant, the pulsed laser beam is guided by the scanner system  100  and/or by the scanner module  12  onto work target points F along the scan line fin such a way that the laser pulse spots P of the pulsed laser beam partly overlap along the scan line f, as a result of which tissue bridges along the scan line f are prevented. The degree of overlap is adjustable depending on the scanning speed of the scanner module  12  and the pulse rate of the laser source  11 . 
     As illustrated schematically in  FIGS.  1  and  2   , the scan length modulator  18  is disposed downstream of the scanner module  12  and configured to modify the length t of the scan line f. In one illustrative example variant, the scan length modulator  18  comprises an adjustable stop to this end, said stop being coupled to an actuatable drive (electric motor). As illustrated schematically in  FIG.  2   , the scan length modulator  18  reduces the length t′ of the scan line f in the deflected laser beam Lf produced by the scanner module  12  to the intended length t of the scan line fin the laser beam Lf′ that is deflected by the scanner module  12  and delimited by the scan length modulator  18 . 
     As illustrated schematically in  FIGS.  1  and  2   , the z-modulator denoted by reference sign  13  is disposed downstream of the scanner module  12  or, in an alternative illustrative example denoted by reference sign  13 ′, it is disposed upstream of the scanner module  12 . The z-modulator  13  and/or  13 ′ is configured to tilt the scan line f out of the x/y-work plane of the scanner module  15 , for example by the tilt angle β, as illustrated schematically in the cross-sectional view B of  FIG.  2   b   , and/or to bend the scan line f with a dynamically modifiable tilt angle β in respect of the x/y-work plane of the scanner module  15 . As illustrated schematically in  FIG.  2   , the z-modulator  13 ,  13 ′ produces a divergence-modulated laser beam Lk with the resultant tilt and/or curvature of the scan line f. 
     In the variant disposed downstream of the scanner module  12 , the z-modulator  13  comprises one or more optical elements disposed upstream of the focusing optical unit  16 , said optical elements being arranged in the beam path from the scanner module  12  to the focusing optical unit  16  and being configured to produce, in the beam path, a divergence of the laser beam L that depends on the scan angle of the scanner module  12 . Illustrative examples of the optical elements of the z-modulator  13  comprise wedge plates, prisms, lenses, diffractive optical elements and aspherical mirrors, for example. The optical elements of the z-modulator  13  are securely installed or, in one variant for setting the divergence of the laser beam L that depends on the scan angle of the scanner module  12 , can be pushed into the beam path and/or pushed out of the beam path. As an alternative, or additionally, the optical elements of the z-modulator  13  can be set or are adjustable for setting the divergence of the laser beam L that depends on the scan angle of the scanner module  12 , for example by rotating the optical elements about the optical axis q, by tilting the optical elements about an axis of rotation or by displacing the optical elements along a translation axis that is tilted in relation to the optical axis q. In an alternative illustrative example variant, the optical element  13  is arranged directly in the scanner module  12  and embodied, for example, as a deflection mirror that has a changeable surface curvature. 
     In the variant disposed upstream of the scanner module  12 , the z-modulator  13 ′ is embodied as a divergence modulator  130  that is configured to dynamically change the divergence of the laser beam L.  FIG.  3    schematically illustrates an illustrative example variant of the z-modulator  13 ′ or the divergence modulator  130  with two optical lenses  131 ,  132  arranged in series, at least one of said lenses being displaceable on an optical transmission axis w for modulating the divergence of the laser beam L. For the purposes of the dynamic modulation of the divergence of the laser beam L, the movable lens  131  is coupled to a movement driver. As is visible in the example of  FIG.  3   , the laser beam L in a first basic position  131 ′ of the movable lens has a corresponding divergence δ 1 . When displacing the movable lens  131  along the transmission axis w, there is a continuous change in the divergence of the laser beam L and it has a modified divergence  62  at the position  131 ″ that is displaced by the deflection distance A. 
     In alternative illustrative example, the z-modulator  13 ′ comprises a spatial light modulator for modulating the wavefront of the laser beam L, a spatial light modulator for modulating the reflection angle at a plurality of points of a reflection face over which the laser beam L is guided, a refractive index modulator for modulating the refractive index of an optical element at a plurality of points in the cross section of the beam path and/or an amplitude modulator for modulating the amplitude at a plurality of points in the cross section of the beam path, i.e. in the beam profile, of the laser beam L. 
     In a further variant, the z-modulator is configured to (adjustably) tilt the focusing optical unit  16  about an axis of rotation that extends perpendicular to a plane defined by the work line s and the optical axis of the focusing optical unit  16  in order thereby to tilt the scan line f out of the x/y-work plane of the scanner module  15  by an adjustable tilt angle. 
     As a result of the divergence modulation, there is a displacement of the focus F of the laser beam L depending on the scan angle of the scanner module  12  in the projection direction and this produces a tilted or curved scan line f. The z-modulator  13 ,  13 ′ or divergence modulator  130  is coupled to the scanner module  12  in such a way that the change in the divergence δ 1 , δ 2  of the laser beam L can be synchronized with the scan angle of the scan movement such that this yields a divergence δ 1 , δ 2  of the laser beam L that changes with the scan angle of the scanner module  12 , i.e., that is dependent on the scan angle. The z-modulator  13 ,  13 ′ and/or divergence modulator  130  is configured to modulate the divergence δ 1 , δ 2  of the laser beam L during the scan movement with a frequency or speed that is at least as large as that with which the scanner module  12  carries out the scan movement over the scan angle in order to bring about a tilt of the scan line f. In order to bring about a “non-linear tilt” and hence a deformation (bend) of the scan line fin the projection direction, the z-modulator  13 ,  13 ′ or divergence modulator  130  is configured to modulate the divergence δ 1 , δ 2  of the laser beam L during the scan movement with frequency components or speed that is greater than that with which the scanner module  12  carries out the scan movement over the scan angle. 
     As illustrated in  FIGS.  1  and  2   , the rotator  14  is disposed downstream of the scanner module  12  in the beam path and configured to rotate the fast-scan plane Lf, which is defined by the scan movement of the scanner module  12  and the optical transmission axis q, about an angle of rotation ϕ about the optical transmission axis q such that a fast-scan plane SE that is rotated through the angle of rotation ϕ is defined, as illustrated schematically in  FIG.  2   . In  FIG.  2   , the laser beam L with the fast-scan plane rotated by the rotator  14  is denoted by the reference sign Lr. In one illustrative example variant, the rotator  14  comprises a K-mirror or a prism for rotating the fast-scan plane Lf. 
     For the better understanding of  FIG.  2   , it should be noted here that a multiplicity of (length-modulated, tilted and rotated) scan lines are reproduced in the schematic illustration of the rotated fast-scan plane SE, said scan lines being produced upstream by the scanner module  12  by deflecting the pulsed laser beam L, being restricted in terms of their length to the length t′ by the scan length modulator  18 , being tilted and/or bent by the z-modulator  13 ,  13 ′ or divergence modulator  130 , and finally being rotated by the rotator  14  about the optical transmission axis q. 
     By controlling the scanner module  12  (fast-scan module) and the scanner module  15  (slow-scan module), the pulsed laser beam is guided in the feed direction v along a work line s onto work target points F in the eye tissue  20  and the eye tissue  20  is scanned in working-on fashion along scan lines f, which, overlaid on the work line s, extend across the work line s. In combination with an appropriate control of the functional modules of the scanner system  100  by the circuit  10 , the scan line f is dynamically set and modified in the process in terms of its length t, t′ by the scan length modulator  18 , in terms of its tilt and/or curvature in relation to the x/y-work plane by the z-modulator  13 ,  13 ′ and in terms of its alignment in the x/y-work plane in relation to the work line s by the rotator  14  such that areas with any predetermined free-form are cut in the eye tissue  20 . By cutting two such cut faces in the eye tissue  20 , lenticules  21  of any predetermined free-form are cut in the eye tissue, as a result of which even the correction of higher order aberrations is facilitated. 
     In the following paragraphs, examples of possible cut methods and cut forms are described with reference to  FIGS.  4 - 16   , said cut methods and cut forms being carried out with an appropriately configured circuit  10  and the control of the ophthalmological apparatus  1  and/or the functional modules of the scanner system  100  carried out therewith. 
     In a cross-sectional view normal to the x/y-work plane,  FIG.  4    illustrates cutting a lenticule  21  in the cornea  22  of an eye  2  by means of a multiplicity of adjoining cut trajectories that are produced by scanning the cornea  22  in working-on fashion using the pulsed laser beam L on work target points F along scan lines f 1 , f 2 , f 3 , f 4 , f 5 , f 6 , f 7 , f 8 , as is visible in the section E illustrated in magnified fashion. Here, the cut trajectories or the scan lines f 1 , f 2 , f 3 , f 4 , f 5 , f 6 , f 7 , f 8  carried out to this end are tilted in each case by a different tilt angle β 5 , β 6 , β 7 , β 8  in relation to the x/y-work plane by means of the z-modulator  13 ,  13 ′, as explicitly specified in the section E, illustrated in magnified fashion, for the cut trajectories or scan lines f 5 , f 6 , f 7 , f 8  of the upper outer face  21   o  of the lenticule and as likewise visible in the cut trajectories or scan lines f 1 , f 2 , f 3 , f 4  of the lower outer face  21   u  of the lenticule  21 . As a result of the individually set tilt angles β 5 , β 6 , β 7 , β 8  of the scan lines f 1 , f 2 , f 3 , f 4 , f 5 , f 6 , f 7 , f 8 , the curve is adapted to the best possible extent to the form (gradient) of the outer faces  21   o ,  21   u  of the lenticule  21  to be cut. The upper and lower outer faces  21   o ,  21   u  meet at the peripheral edge  21   r  of the lenticule  21  to be cut, which is embodied as a cylindrical area in one variant. 
     In the plan view of the x/y-work plane,  FIGS.  5 ,  6 ,  7 ,  8 ,  9  and  10    illustrate different work lines s for cutting the lenticule  21  in the cornea  22  of an eye  2  by means of scan lines f, which are overlaid on the respective work lines s and (as illustrated in  FIG.  2   a   ) have an orientation angle ϕ′ in relation to the work line s. As is visible in  FIGS.  5 ,  6 ,  7 ,  8 ,  9  and  10   , the work lines s extend across the meridians m of the lenticule  21 ; i.e., the work lines s do not extend along the meridians m of the lenticule  21  but instead cut at least one of the meridians m of the lenticule  21 . The work lines s according to  FIGS.  5 ,  6 ,  9  and  10    each extend in the x/y-work plane, to be precise at different heights or depths in the z-direction, but there is no need for a change in the z-direction while scanning a closed work line s by the second scanner module  15 . In the work lines s according to  FIGS.  7 ,  8 ,  12  and  13   , an adjustment in the z-direction is required while scanning a work line s by the second scanner module  15 . Depending on the illustrative example of the second scanner module  15 , the z-component of these height-varying work lines s are adapted to the outer faces  21   o ,  21   u  by an appropriate control of the second scanner module  15  or a separate focusing apparatus by way of the circuit  10 . In a further illustrative example variant, an adjustable optical unit (e.g. with displaceable lenses) that is disposed upstream of the focusing optical unit  16  and disposed upstream or downstream of the z-modulator  13 ,  13 ′ is provided to this end, said adjustable optical unit being configured to displace the scan line f that was tilted or bent by the z-modulator  13 ,  13 ′ vertically in the z-direction. However for the purposes of improved understanding, it should be noted here that such adjustable optical units cannot fulfil the advantage of the z-modulator  13 ,  13 ′ or divergence modulator  130  as, firstly, they are not synchronized with the scanner module  12  and, secondly, they also cannot carry out a focus displacement in the z-direction sufficiently quickly in order to be able to be synchronized with the scan movement or the corresponding scan angle of the scanner module  12  (fast-scan module). Also, these adjustable optical units do not facilitate an adjustable tilt of the scan line f, as is achieved by the variant in which the z-modulator tilts the focusing optical unit  16  about an axis of rotation. 
       FIG.  5    shows a cut implementation with a plurality of circular work lines s that are arranged concentrically to the optical axis of the eye  2 .  FIG.  6    shows a cut implementation with a plurality of elliptical work lines s that are arranged concentrically to the optical axis of the eye  2 .  FIG.  7    shows a cut implementation with a spiral work line s with a centre of the spiral on the optical axis of the eye  2 .  FIG.  8    shows a cut implementation with a plurality of spiral-arm-shaped work lines s that run towards a centre point on the optical axis of the eye  2  proceeding from the peripheral edge  21   r  of the lenticule  21  (or vice versa).  FIG.  9    shows a cut implementation with a plurality of elliptical work lines s that are arranged concentrically to the optical axis of the eye  2 , with the longitudinal and transverse axes of the lenticule  21   s  being rotated in the x/y-work plane about the optical axis of the eye  2 , as indicated by the arrow  3 , in contrast to the lenticule  21  of  FIG.  6   .  FIG.  10    shows a cut implementation with a plurality of work lines s, which are each defined by a free-form closed curve. 
     Compared to the cut implementation according to  FIGS.  5  and  6   , the cut implementation according to  FIG.  7    is advantageous in that it facilitates a slow and continuous height adjustment of the work line s, and hence of the scan line f extending thereacross, when cutting a (three-dimensional) lenticule  21 ; that is to say, it is possible to dispense with discontinuous and faster changes in the z-direction. 
     The advantage of the cut implementation according to  FIGS.  8  and  12    consists of no periodic structures, which could lead to bothersome influences on the imaging when seeing, being produced in relation to the optical axis of the eye  2  since the rotation of the scan line f has a lower measure of preferred (accumulated) orientation (alignment). 
     As illustrated in  FIGS.  5 ,  6 ,  7 ,  8 ,  9  and  10   , the alignment or the alignment angle ϕ′ of the scan line fin relation to the work line s by way of the rotator  14 , controlled by the circuit  10 , is dynamically modified and set during the work depending on the current position of the work target point F on the work line s. Thus, in the cut implementation of  FIG.  5   , the scan lines f 9 , f 10  each have an alignment angle ϕ′ of 90°, i.e. a normal alignment of the work line s, which is achieved by the rotator  14  by continuous adjustment and adaptation of the angle of rotation ϕ to the work line s. 
     In the cut implementation according to  FIG.  6   , the scan line  11  is aligned in relation to the work line s with an alignment angle ϕ′ 1  that is not rotated normally in relation to the work line s such that, in comparison with a scan line f that is aligned normally to the work line s, a narrower work trajectory or cut trajectory is produced in the narrower region of the elliptical lenticule  21  during the work. The scan line f 12  is aligned normally to the work line s with the alignment angle ϕ′ 2  in order to produce a wider work trajectory or cut trajectory in the longer region of the elliptical lenticule  21 . Finally, the scan line f 13  is aligned normally to the work line s with the alignment angle ϕ′ 3 ; however, in comparison to the scan lines f 11  and f 12 , it has a shorter length t, set by the scan length modulator  18 , in order to produce a narrower work trajectory or cut trajectory in the narrower region of the elliptical lenticule  21  during the work. 
     In the cut implementations according to  FIGS.  7  and  9   , too, the scan lines overlaid on the spiral work line s or the elliptical work lines s are in each case dynamically modified and set in respect of their alignment angle ϕ′ to the work line s, their length t and/or their tilt angle β or their curvature during the work depending on the current position of the work target point F on the work line s in order to produce the lenticule  21  with spiral or elliptical work trajectories or cut trajectories. 
     In the cut implementation according to  FIG.  8   , the alignment angle ϕ′, the length t and the tilt angle β or the curvature of the scan line f 12 , f 13 , f 14  are each dynamically modified and set during the work depending on the current position of the work target point F on the spiral arm in order to produce the lenticule  21  with spiral-arm-shaped work trajectories or cut trajectories, the width of which proceeding from the peripheral edge  21   r  of the lenticule  21  reduces towards the centre point on the optical axis of the eye  2 , or the width of which increases again from the centre point towards the peripheral edge  21   r.    
     In the cut implementation according to  FIG.  10   , the scan lines overlaid on the work lines s are in each case dynamically modified and set in respect of their alignment angle ϕ′ to the work line s, their length t and their tilt angle β or their curvature during the work depending on the current position of the work target point F on the work line s in order to produce the lenticule  21  with a predetermined free-form for correcting a higher-order aberration. 
     In the cut implementation according to  FIG.  12   , the alignment angle ϕ′ and the length of the scan line F 12 , F 13 , F 14  are each dynamically modified and set depending on the current position of the work target point F on the spiral arm s 1 , s 2  during the work, like in the example of  FIG.  8   , in order to produce the lenticule  21  with spiral-arm-shaped work trajectories or cut trajectories, the width of which proceeding from the peripheral edge  21   r  of the lenticule  21  reduces towards the centre point on the optical axis of the eye  2 , or the width of which increases again from the centre point towards the peripheral edge  21   r . However, in contrast to the illustrative example according to  FIG.  8   , the spiral-arm-shaped work lines s 1 , s 2  are not guided up to the centre point on the optical axis of the eye  2  but are guided around the centre point, forming a round clear space M and maintaining a predetermined distance from the centre point, such that a spiral arm s 1  proceeding from the peripheral edge  21   r  is guided up to the edge of the clear space M and is guided proceeding therefrom to the peripheral edge  21   r  of the lenticule  21  again as a spiral arm s 2  (or vice versa). Here, the length of the scan lines overlaid on the spiral work lines are set in such a way at the edge of the clear space M that as few overlaps as possible are caused by the scan lines when working on the clear space M. 
       FIGS.  13  and  14    show a cut implementation with a plurality of work lines s that extend in planes extending parallel to the optical axis of the eye  2  and that each cut a plurality of meridians m of the lenticule  21 . The scan lines f 17 , f 18  overlaid on the work lines s are each aligned with an alignment angle ϕ′ of 90°, i.e. normal to the relevant work line s. As schematically illustrated in the cross section in  FIG.  14   , the scan lines f 17 , f 18  are each tilted out of the x/y-work plane with a tilt angle β 17 , β 18  in order to adapt these to the curve of the upper and lower outer faces  21   o ,  21   u , to be cut, of the lenticule  21 . 
       FIG.  11    shows, in a cross section, a cut implementation of a lenticule  21  with an upper and lower outer face  21   o ,  21   u  and a peripheral edge  21   r  which, in the applanated state of the cornea, are cut into the eye tissue of the cornea  2  for the purposes of correcting hyperopia. The upper and lower outer face  21   o ,  21   u  of the lenticule  21  are cut using a cut implementation according to one of  FIG.  5 ,  6 ,  7 ,  8 ,  9 ,  10 ,  12  or  14   . The peripheral edge  21   r  is cut with a scan line that is tilted out of the x/y-work plane by 90°, said scan line being overlaid on a work line s that extends around the lenticule  21  to be cut in the peripheral edge  21   r.    
     For better understanding, it should be noted here that the upper and lower outer face  21   o ,  21   u  of the lenticule  21  illustrated in  FIG.  4    in cross-section, too, are cut in the non-applanated state of the cornea  2  with a cut implementation according to one of  FIG.  5 ,  6 ,  7 ,  8 ,  9 ,  10 ,  12  or  13   / 14 . The same applies to the cut methods explained below according to  FIGS.  17  and  18   . 
     In the following paragraphs, the implementation and production of an areal cut in the eye tissue  20 , controlled by the circuit  10 , and the cut implementation and production of a lenticule in the eye tissue  20 , controlled by the circuit  10 , are illustrated with reference to  FIGS.  17  and  18   . 
     In order to cut an area in the eye tissue  20 , the circuit  10  controls the scanner system  100  and/or the optical functional modules thereof in order to guide the pulsed laser beam onto work target points F in the eye tissue  20 . For the purposes of producing the cut area, the circuit  10  controls the scanner system  100  in step S 1  in such a way that the pulsed laser beam scans the eye tissue  20  in work trajectories that extend parallel next to one another or that extend next to one another and have a spiral, circular or elliptical form. In the process, the second scanner module  15  of the scanner system  10  guides the pulsed laser beam in the feed direction v onto work target points F along a work line s and the first scanner module  12  of the scanner system  100  guides the pulsed laser beam onto work target points F along a scan line f that extends across the work line s, as illustrated in  FIGS.  2   a ,  2   b    and  4 - 14  and as described above with reference to these figures, and so a cut trajectory defined by the work trajectory is produced in step S 11 . 
     In step S 11 , the circuit  10  controls the scanner system  100  and/or the optical functional modules thereof in such a way that the cut trajectories are produced in a plurality of work trajectories, wherein tissue bridges that remain in each case are left between the cut trajectories. This is illustrated in  FIG.  15    using the example of spiral work lines and spiral work trajectories and the resultant cut trajectory  30  defined thereby. The work trajectories  3  extending next to one another are visible in the upper part of  FIG.  15   . As is visible in a section illustrated with magnification in the lower part of  FIG.  15   , the work trajectories  3  extending next to one another are worked on in step S 11  in such a way that cut trajectories  30  are produced in the worked-on work trajectories, said cut trajectories being separated by tissue bridges  31  in interposed, not yet worked on work trajectories. Depending on the form of the work line s, the work trajectories  3  and/or cut trajectories  30 , based thereon, extend parallel next to one another or extend next to one another in a spiral, circular or elliptical fashion, or in free-form closed curves. 
     In optional step S 12 , the circuit  10  controls the measurement system  17  in such a way that the latter captures the produced cut trajectories  30  and determines the remaining tissue bridges  31  on the basis of the produced cut trajectories  30 . On account of the determined tissue bridges  31 , the circuit  10  determines the not treated work trajectories yet to be treated. In  FIG.  15   , reference sign  32  relates to a captured portion of the produced cut trajectories  30   a ,  30   b  for determining the interposed tissue bridge  310  and the yet to be worked on corresponding work trajectory. In the case of the measurement system  17  embodied as an interferometric measurement system, in particular, the capture of the produced cut trajectories  30   a ,  30   b  and the determination of the interposed tissue bridge  310  for positioning the work trajectory to be worked on is carried out continuously during the work (“online”), and so the current work target point F of the work line s or of the scan line f aligned thereacross, in the work direction v, follows (“upstream”) the captured portion  32  (“downstream”) of the produced cut trajectories  30   a ,  30   b.    
     In step S 13 , the circuit  10  controls the scanner system  100  and/or the optical functional modules thereof in such a way that the specific tissue bridges  31  or the yet to be treated work trajectories are worked on. Expressed differently, the scanner system  100  is controlled in such a way that it guides the pulsed laser beam onto work target points F into the tissue bridges  31  remaining between the cut trajectories  30  in order to complete the tissue cut. In one illustrative example variant, the tissue bridges are worked on in work trajectories  3 , the width of which goes beyond the width of the specific tissue bridges  31 . Once all remaining tissue bridges  31  have been worked on, the area is completely cut and the corresponding cut area is produced in the eye tissue  20 . 
     Two cut areas, the lower outer face  21   u  and the upper outer face  21   o  of the lenticule  21  are cut in the eye tissue for the purposes of cutting a lenticule  21 . 
       FIG.  18    illustrates a cut method in which a lenticule  21  in the eye tissue  20  is cut in a sequence of cut sequences. Here, the circuit  10  controls the scanner system  100  and/or the optical functional modules thereof in such a way that, in step S 2 , the work trajectories  30  on the lower outer face  21   u  of the lenticule  21  to be cut are worked on and, in step S 21 , the cut trajectories  30  with remaining tissue bridges  31  are produced, as described above with respect to  FIG.  17    in conjunction with steps S 1  and S 11 . Expressed differently, the lower outer face  21   u  of the lenticule  21  is initially cut incompletely in steps S 2 , S 21  with remaining tissue bridges  31  between the cut trajectories  30 . 
     In contrast to cutting the cut area according to  FIG.  17   , cutting the upper outer face  21   o  of the lenticule  21  is started first in the subsequent step S 3 . Here, the circuit  10  controls the scanner system  100  and/or the optical functional modules thereof in such a way that, in step S 3 , the work trajectories  30  on the upper outer face  21   o  of the lenticule  21  to be cut are worked on. To this end, in optional step S 31 , the circuit  10  controls the measurement system  17  in such a way that the latter captures the cut trajectories  30  on the lower outer face  21   u  that were produced in step S 2  and/or S 21  and determines the work trajectories  3  to be worked on or the cut trajectories  30  to be cut on the upper outer face  21   o  on the basis of the produced cut trajectories  30  of the lower outer face  21   u . Here, in addition to the lateral positioning of the upper outer face  21   o  with respect to the lower outer face  21   u , a predetermined centre thickness d and/or a predetermined thickness profile D of the lenticule  21  to be cut is also observed. In one illustrative example variant, the circuit  10  moreover controls the measurement system  17  in such a way that the measurement system  17  captures deformations in the eye tissue that were caused by gas bubbles produced when cutting the cut trajectories  30  on the lower outer face  21   u , and the upper outer face  21   o , or the work trajectories  3  to be worked on and, as a result thereof, cut trajectories  30  to be cut on the upper outer face  21   o  are positioned taking account of the captured deformations in respect of the captured lower outer face  21   u . Then, the circuit  10  controls the scanner system  100  and/or the optical functional modules thereof in such a way that, in step S 32 , the cut trajectories  30  are produced with remaining tissue bridges  31  on the upper outer face  21   o , as described above with reference to  FIG.  17    in conjunction with steps S 1  and S 11 . In one illustrative example variant, the circuit  10  determines the work trajectories  3  for producing the cut trajectories  30  on the upper outer face  21   o  with a smaller trajectory width in respect of the captured cut trajectories  30  on the lower outer face  21   u . In step S 32 , the upper outer face  21   o  of the lenticule  21  is also cut in incomplete fashion with remaining tissue bridges  31  between the cut trajectories  30 . 
     In subsequent step S 4 , the tissue bridges  31  remaining on the lower outer face  21   u  between the cut trajectories  30  are cut. To this end, the circuit  10  controls the scanner system  100  and/or the optical functional modules thereof in such a way that, in step S 4 , the work trajectories  30  with the remaining tissue bridges  31  on the lower outer face  21   u  of the lenticule  21  to be cut are worked on. In optional step S 41 , the circuit  10  controls the measurement system  17  in such a way that the latter captures the already produced cut trajectories  30  on the lower outer face  21   u  and determines the remaining tissue bridges  31  on the basis of the captured cut trajectories  30 . On account of the determined tissue bridges  31 , the circuit  10  determines on the lower outer face  21   u  the not treated work trajectories yet to be treated. In step S 42 , the circuit  10  controls the scanner system  100  and/or the optical functional modules thereof in such a way that the remaining tissue bridges  31  or the yet to be treated work trajectories are worked on and cut as a result thereof, as described above with respect to  FIG.  17    in conjunction with step S 13 , and, as result thereof, completes the tissue cut on the lower outer face  21   u  of the lenticule  21 . 
     In subsequent step S 5 , the tissue bridges  31  remaining on the upper outer face  21   o  between the cut trajectories  30  are cut. To this end, the circuit  10  controls the scanner system  100  and/or the optical functional modules thereof in such a way that, in step S 5 , the work trajectories  30  with the remaining tissue bridges  31  on the upper outer face  21   o  of the lenticule  21  to be cut are worked on. In optional step S 51 , the circuit  10  controls the measurement system  17  in such a way that the latter captures the already produced cut trajectories  30  on the upper outer face  21   o  and determines the remaining tissue bridges  31  on the basis of the captured cut trajectories  30 . On account of the determined tissue bridges  31 , the circuit  10  determines on the upper outer face  21   o  the not treated work trajectories yet to be treated. In step S 52 , the circuit  10  controls the scanner system  100  and/or the optical functional modules thereof in such a way that the remaining tissue bridges  31  or the yet to be treated work trajectories are worked on, as described above with respect to  FIG.  17    in conjunction with step S 13 , and, as result thereof, completes the tissue cut on the upper outer face  21   o  of the lenticule  21 , as a result of which the lenticule  21  is completely cut.