in a next step , objective and subjective refraction data , namely the spherical and cylindrical refraction of the patient , are established . objective refraction data are data which are established exclusively by measuring with a measuring apparatus . this can be for example by means of a refractometer or aberrometer . subjective refraction data are data which are based on the feedback from the patient , who reports whether a potential correction is found to be “ better ” or worse . this is achieved for example by using a phoropter which displays potential correction scenarios on which the patient comments . with refractive correction of the cornea based on aberrometric wave - front data it must be taken into account that an aberrometer measurement is an objective measuring process . however , due to the physiological process of vision , the quality of the individual sight is ultimately fixed , not only by the objective optical quality of the optical system , the eye , but additionally by the subjectively evaluated visual faculty . with the device according to the invention and the method according to the invention , it is provided to also allow , in addition to aberrometry , topography , pachymetry , pupillometry , fixing / centring , registration ( this is a point - accurate allocation of the measurement data of the eye to position the therapeutic correction , e . g . via local marks on the cornea or significant structures of the eye such as veins or iris structures ) and phoropter , a subjective evaluation of the refraction with the help of a phase - plate or adaptive phoropter and an acuity projector to play a part . in a simplified method the subjective evaluation of the higher - order aberrations can be excluded , e . g . by means of zernike polynomials , using the sphere and cylinder values determined with a refractometer and / or subjectively evaluated with a phoropter as a base data set for the refractive correction . in addition this base data set is supplemented by the objectively measured data of higher - order zernike polynomials which are corrected by the spherical equivalent portions from the wave - front data . the higher aberration orders have a particular role in the production of aspherical lens profiles or correction profiles . the simplified method represented above can also be carried out directly on the basis of height data instead of the wave - front / data calculation based on zernike polynomials . these aberrometer - aided height data are customary in the measurement data output of topography equipment and are obtained in aberrometers with the help of “ zonal reconstruction ”. compared with data exchange on the basis of zernike polynomials , they guarantee a higher spatial resolution of the wave front . uncertainties with regard to the correct wave - front reconstruction in polynomial description can be largely avoided depending on the resolution of the zonal reconstruction . so - called “ repair cases ” can thus be realized based on a complete data set of the overall optical system . also on the basis of these wave - front height data , it must be taken into account within the framework of the described simplified method that in addition to the base data set the wave - front data can also be supplemented as equivalent portions without the spherical and cylindrical base portions . in individually optimized treatment based on the method according to the invention , a higher quality of the refractive correction of the cornea is achieved in particular by combining the produced measurement data of the whole wave front and the topography of the cornea based on a polynomial breakdown , e . g . according to zernike or taylor and / or the height data . in this way , the refractive correction can be designed in consideration of the special characteristics of the different optical part - systems of the eye . particular consideration is given to the cornea which delivers the main refracting power of the eye at approx . 80 % and simultaneously forms the ablation target for refractive laser surgery . thus in a simplified model the projection effects of the ablative laser spot on the spherical surface of the cornea can be taken into account for a radius of approx . 7 . 8 mm over a keratometric radius measurement of the cornea . a still more precise control of the ablation in consideration of the projective fluence variations of the laser spot on the cornea is obtained when the topography is taken into account . thus not only can the ablation be controlled by the method according to the invention , in consideration of a keratometrically established radius of the cornea in order to balance out the projective fluence variations of the laser spot in particular at the margins of the ablation , but the topography data which describe the surface more accurately can also be used for this . the higher - order aberrations are objectively established by means of a wave - front measurement . known devices and methods for wave - front measurement can be used for this . in a further step , height data of the deviations of the cornea surface relative to a reference surface are calculated from the thus - established refraction or topography data . they are established from refraction data , applying the standard algorithms , for example the munnerlyn formulae . a sphere is used as assumed reference surface . in a further step the height data are derived from the topography data . the curvature of the reference surface is established using the refraction data . here too the data are calculated using standard algorithms such as munnerlyn formulae . the k values are also taken into account here . an ellipsoid is used as assumed reference surface . in a further step , the refraction data are linked to the data of the wave - front measurement . the curvature of the reference surfaces is established using the refractive data . the subjective refractions are calculated applying standard algorithms such as the munnerlyn formulae and overlaying the thus - established data with high - order ( ho ) data . a sphere is used as assumed reference surface . in a third step the refraction data are linked to the topography data and the data of the wave - front measurement . here too these values are overlaid with high order data in consideration of the k values applying standard algorithms such as the munnerlyn formulae . an ellipsoid is used here as assumed reference surface . the difference in the topography data vis - à - vis the data established with the wave front measurement is problematic . in a further step the height data difference relative to the reference surface is now calculated . a chart ( data map ) is calculated with height data relative to the deviations to the reference surface . the height difference relative to the reference surface , and thus the tissue to be abraded is given for each point of the cornea surface . when applying the lasik procedure , the flap thickness , the flap diameter and the direction of the fold ( hinge side ) of the flap are determined . furthermore , data relating to pachymetry , the thickness of the cornea , are included in the form of a pachymetry map . the effects of pachymetry on the ablation depth are determined . in addition , further patient data such as the age and the cylinder data of the patient are included . effects on the correction of the refraction and correction of the cylinder axis are also calculated from these . depending on the method to be carried out , for example prk or lasik , process - typical effects on the nomograms and the refraction are established . in addition certain optimizations are taken into account , e . g . tsa , night vision , asap grade . a reference surfaces fit is brought about in each zone with a z shifting . with the parameters shown above , patient - adapted ( customized ) height data differences relative to the reference surface are established from the height data difference relative to the reference surface . this results in an adapted data map with height data of the deviation relative to the reference surface . the ablation algorithms are realized with these data . this produces as a result the output of the residual thickness , the ablation volume and the residual defect . in addition to the previously established data the influences of the laser parameters , in particular the energy density distribution , the firing frequency , the spot geometry and also the resolution accuracy of the scanner are taken into account . in addition the data with regard to smoke and thermal problems are incorporated . in addition , reflection and projection data are established , in particular the change in energy density distribution and reflection losses . this yields correction data for the ablation target data . finally , ablation coordinates for the laser are issued , in this case coordination data for specific lasers ( for example mel 70 ). the established and calculated data can be issued on a computer screen in the form of a graphic simulation . the simulation displays the cornea to be treated for example in different colours or similar in top view or in section so that the doctor in attendance can assess the whole procedure in advance . thus it is possible with this device or the electronic data - processing system which consists either of a networked or compact integrated measuring equipment system to record all the objective and subjective data of the optical refraction and geometry of the eye is such a way that they are stored or displayed overlaid centred and point - accurate in a fixed coordinates system of the eye .
a method for controlling a device for the treatment or refractive correction of the human eye using an electronic data processing system provides a simple overview of the influence of all of the parameters . to this end , once the operating parameters have been determined , a graphical simulation of the operating procedure is carried out in the form of a graphical visualization .