the method according to the invention will now be explained with reference to fig1 . a method for multifocal corneal surgery for the correction of presbyopia is described . this method for the correction of presbyopia can be performed in emmetropic eyes , i . e . in eyes that are exclusively presbyopic but that otherwise have normal vision , and also in shortsighted ( myopic ), farsighted ( hyperopic ) and / or astigmatic eyes that are additionally presbyopic . at this juncture , it should be pointed out that the flow diagram according to fig1 exclusively shows the method for emmetropic eyes . there are further method steps in the case of eyes with additional visual inadequacies . as can be seen in fig1 , the method starts in that the near vision and the distance vision in the eye that is to be treated are measured ( step 100 ). then the pupil size , i . e . the diameter of the pupil in daylight ( photopic ) as well as under dusk conditions ( mesopic ) is determined ( step 200 ). then , if applicable , the values for a standard correction ( sphere , cylinder , axis ) are measured if corresponding “ standard visual inadequacies ” ( myopia , hyperopia , astigmatism ) are present . in order to correct the presbyopia , the higher aberrations and the k - values are measured ( step 300 ). then , on the basis of the ascertained mesopic pupil , the optical zone of the treatment is determined ( step 400 ), the optical zone being the effective optical zone without a transition zone . on the basis of the measurements taken , the profile change to be made to the cornea of the eye can now be calculated . in order to correct the presbyopia , a profile change is calculated that consists of two components . here , to start with , a first profile component is calculated from the preoperative spherical aberration , from the presbyopia addition and from the daylight pupil as the target for the spherical aberration ( step 500 ). this first component exhibits a higher refractive power centrally in the range of the daylight pupil than in the range between the daylight pupil and the mesopic pupil . here , the zernike polynomials are used in order to calculate this first component . the first profile component is calculated from the z ( 4 . 0 ), the z ( 6 . 0 ) and possibly other higher - order zernike polynomials . in addition to the first component , however , a myopic component is needed , which compensates for the refractive change caused as an undesired side effect by the first component ( step 600 ). for this purpose , a z ( 2 . 0 ) term in the order of magnitude of the presbyopia addition is employed . the sum of the determined first and second components form the portion of the profile change that serves to correct the presbyopia . moreover , a third component for the profile change is also calculated ( step 700 ). this third component provides the transition zones at the edge of the profile change in order to avoid greater angle changes of the cornea surface . finally , if applicable , on the basis of the values for a standard correction , a fourth component is formed for correcting myopia , hyperopia and / or astigmatism . the calculated profile components are finally combined to form a total profile change ( step 800 ). then this total profile change — consisting of z ( 2 . 0 ), z ( 4 . 0 ), z ( 6 . 0 ), a transition zone and , if applicable , a standard correction — is converted into an ablation program for an ablative excimer laser ( step 900 ). however , such a total profile change is only possible if the calculation or treatment diameter is selected to be the same for all of the components . however , it is also conceivable to dispense with the formation of a total profile change and to remain with a two - part treatment , for example , along the lines that the basic correction ( myopia , hyperopia , astigmatism ) is contained in one part and the presbyopia correction is in a second part with a different diameter . reasons for different diameters can be , for instance , that , due to insufficient corneal thickness , the basic correction in cases of severe visual inadequacies can only be carried out with a smaller diameter than the pupil diameter would require for the presbyopia portion . thus , greater variability of the surface is achieved , which can no longer be described only by zernike polynomials up to the fourth order . during the conversion into an ablation program , the local k - value of the cornea is taken into account so that this ablation program does not induce any uncontrolled spherical aberrations . a device 1 for carrying out the method just described is presented on the basis of fig2 . the device 1 comprises a light source or radiation source 2 , a beam modification device 3 , a wavefront analysis device 4 , a topography analysis unit 5 , a means 6 for measuring the photopic and mesopic pupil diameter and a means 7 for deriving a photo - ablation profile . the radiation source 2 is preferably a laser , especially a refractive laser . as a rule , a spot scanning excimer laser system is provided as the radiation source 2 . as an alternative , the laser can also be an fs - laser . the beam - forming and guide system 3 serves to form and deflect a beam 8 of the radiation source 2 . in order to form the beam 8 , the device 3 preferably has lens systems , diffractive or refractive micro - optical elements . in order to collimate and deflect the beam , the device 3 preferably has scanner arrays , prisms or mirrors . the wavefront analysis device 4 serves to analyze the wavefront of the optical path in the eye . the topography analysis unit 5 serves to analyze the cornea surface of the eye . the means 7 for deriving the photo - ablation profile , which can also be designated as a calculation unit , has the task of calculating an appropriate ablation profile on the basis of the wavefront measured by the wavefront analysis device 4 , on the basis of the topography measured by the topography analysis unit 5 , and on the basis of the pupil diameter measured by the means 6 for measuring the photopic and mesopic pupil diameter . the data needed for this is supplied to the calculation unit 7 by the measuring units 4 , 5 and 6 via suitable interfaces 9 a , 9 b and 9 c . the calculation unit 7 also controls the actual ablation process . the process and the appertaining device described here yield an ablation program that results in an improvement of the focal depth of the optically active zone of the cornea and thus to an improvement of the near vision . in contrast to the state of the art , this is attained in a way that the distance vision is not impaired . the distance vision remains refraction - neutral . since moreover , according to the invention , two pupil sizes ( light and dark ) are taken into consideration , a more individual optimization is achieved . the additional introduction of transition zones contributes to the reduction of undesired side effects that are referred to as glare and halo ( glare or halo after eye surgery means that the patient perceives a disturbing shining , flashing , brightness , aura or sparkling , for example , around sources of light ). the creation of defined multifocality via the higher order of the spherical aberration prevents the sharp transitions of true bifocal zone divisions that evolve into undefined multifocality through later epithelial compensation .
a method for changing a property of an eye uses a continuously multifocal profile that includes a component for increasing a focal depth . the method includes calculating the component for increasing the focal depth to be rotation - symmetrical . alternatively , or in addition , the calculating is carried out so as to optimize an encircled energy criterion over an extended range of depth .