PLANNING DEVICE AND METHOD FOR GENERATING CONTROL DATA FOR AN EYE SURGERY TREATMENT DEVICE

Description

[0001] The invention relates to a planning device for generating control data for a treatment device that creates at least one incision in the cornea by means of a laser device. The invention further relates to a treatment device having a planning device of the aforementioned type.

[0002] The invention further relates to a method for generating control data for a treatment device which creates at least one incision in the cornea by means of a laser device.

[0003] Also described is a method for eye surgery, which is not part of the invention, wherein at least one incision is made in the cornea by means of a treatment device with a laser device.

[0004] A wide variety of treatment procedures are known in the state of the art for the purpose of correcting refraction in the human eye. The aim of the surgical methods is to specifically alter the cornea in order to influence the refraction of light in the eye. Several surgical techniques are used for this purpose. The most common at present is so-called laser in situ keratomileusis, also abbreviated to LASIK. In this procedure, a corneal flap is first detached from the surface of the cornea on one side and folded to the side. This lamella can be detached using a mechanical microkeratome or a so-called laser keratome, such as that sold by Intralase Corp., Irvine, USA. After the lamella has been detached and folded to the side, the LASIK procedure involves the use of an excimer laser to ablate the corneal tissue thus exposed beneath the lamella.After the volume beneath the corneal surface has been evaporated in this way, the corneal flap is folded back into its original position.

[0005] The use of a laser keratome to expose the lamella is advantageous over a mechanical knife because it improves geometric precision and reduces the incidence of clinically relevant complications. In particular, the lamella can be created with a much more consistent thickness when laser radiation is used. The incision edge is also precisely shaped, which reduces the risk of impaired healing caused by this interface that remains even after surgery. A disadvantage of this procedure, however, is that two different treatment devices must be used: the laser keratome to expose the lamella, and the laser that vaporizes the corneal tissue.

[0006] These disadvantages have been eliminated by a procedure recently implemented by Carl Zeiss Meditec AG. In this procedure, commonly referred to as lenticule extraction, a short-pulse laser, preferably a femtosecond laser, is used to create an incision geometry in the cornea, which separates a corneal volume (the so-called lenticule) within the cornea. This is then manually removed by the surgeon. The advantage of this procedure is that the incision quality is further improved by the use of the femtosecond laser.

[0007] Secondly, only one treatment device is required; the excimer laser is no longer used.

[0008] A medically advantageous variant of the procedure is referred to in the literature as the SMILE procedure. In this procedure, no flap is created, but only a small incision is made to access the lenticule located beneath the cap. The separated lenticule is removed through this small incision, which means that the biomechanical integrity of the anterior cornea is less compromised than with other procedures. In addition, fewer superficial nerve fibers in the cornea are severed in this way, which has a demonstrably positive effect on restoring the original sensitivity of the corneal surface. The symptom of dry eyes, which is often treated after LASIK, is thus reduced in severity and duration. Other complications after LASIK that are usually related to the flap (e.g., wrinkles, epithelial ingrowths in the flap bed) also occur less frequently without a flap.

[0009] When creating incisions in the cornea using laser radiation, the optical radiation effect is typically exploited by generating an optical breakthrough through individual optical pulses whose duration can range between approximately 100 fs and 100 ns. It is also known to introduce individual pulses, whose energy lies below a threshold for optical breakthrough, into the tissue or material in such a way that material or tissue separation is also achieved. This concept of creating incisions in corneal tissue allows for a wide variety of incisions.

[0010] It is also state of the art to perform refractive correction by inserting an implant (also called an inlay) into the cornea of at least one eye of an affected patient. The implant can be artificial, e.g., a ring or lens made of a plastic material (e.g., KAMRA ®< , Flexivue ®< ), or a suitably shaped implant made of a biomaterial or a transplant of human corneal tissue.

[0011] For the implants currently available, it is common practice to create a pocket-like incision geometry (pocket) in the cornea using a femtosecond laser keratome, which is designed to accommodate the implant and at the same time supports the insertion of the implant by the physician.

[0012] Lenticle extraction procedures generally offer good opportunities for combination with an implantation procedure, whereby an implant is placed inside the cornea following lenticule removal. The SMILE procedure also offers the possibility of utilizing the pocket-like incision geometry created as a result of the procedure to accommodate the implant, thus providing a certain degree of mechanical stability.

[0013] However, it has been shown that the success of such refractive correction does not always meet expectations, and a (albeit minor) refractive error remains after treatment. It is currently possible to use known surgical correction procedures (PRK or LASIK with excimer laser) to refractively correct affected eyes before or after inlay implantation (re-correction).

[0014] If the correction is carried out using one of the correction procedures mentioned, the removal of tissue covering the implant and the direct interaction of the therapeutic radiation with the inlay represent a certain risk for the effectiveness and safety of the overall procedure.

[0015] In another area of ophthalmology, namely the treatment of presbyopia, it is known to make concentric incisions in the cornea to alter its mechanical stability. One such solution is described, for example, in US Pat. No. 7,717,907, where the incisions extend to a depth of 90% of the corneal thickness. These deep incisions cause changes in corneal curvature through the interaction of intraocular pressure and reduced counterforces throughout the cornea (induced keratoconus).

[0016] The invention is therefore based on the object of specifying a planning device for generating control data, a treatment device for refraction-correcting eye surgery and a method for generating control data for such a treatment device, in which a reliable subsequent correction after provision with a corneal implant is ensured.

[0017] This object is achieved according to the invention with a planning device of the type mentioned at the outset, which has calculation means for determining at least one corneal incision, wherein the calculation means determine the corneal incisions in such a way that the refractive errors existing after the introduction of an implant into the cornea are counteracted.

[0018] The invention is further achieved with a treatment device which has a laser device which makes at least one incision in the cornea by means of laser radiation according to control data, and has a planning device of the type just mentioned for generating the control data, wherein the planning device determines the corneal incisions in such a way that the refractive errors existing after insertion of an implant into the cornea are counteracted.

[0019] Finally, the invention is also achieved with a method for generating control data according to the type mentioned at the outset, which comprises: generating a control data set for the corneal incisions for controlling the laser device, wherein the planning device determines the new corneal incisions in such a way that existing refractive errors are counteracted after the introduction of an implant into the cornea.

[0020] Furthermore, a non-claimed method is described, which comprises: generating a control data set for the corneal incisions, transmitting the control data to the treatment device and generating the incisions by controlling the laser device with the control data set, wherein during the generation of the control data set the new corneal incision is determined in such a way that the refractive errors existing after insertion of an implant into the cornea are counteracted.

[0021] A suitable device for this purpose is described in DE 10 2007 019 815 A1 and DE 10 2013 218 415 A1 by the applicant. US 2012 / 172854 A1 mentions corneal relief incisions in connection with corneal transplants.

[0022] The method and the corresponding device according to the invention cause changes in the shape of the cornea through the interaction of the forces caused by the implanted lenticule (implant) and the reduced counterforces in the anterior cornea of the cap, ie the part of the cornea lying above the implant.

[0023] These incisions (hereinafter also referred to as relief incisions) are made particularly close to the Bowman's membrane and can cut through it. They do not extend deeper than the pocket incision, i.e., no deeper than the depth of the implant.

[0024] It is advantageous if the incisions do not extend deeper than 80% of the cap's thickness into the cornea. Furthermore, it is best if the incisions are made entirely within the cornea. This prevents openings in the overlying tissue, which could adversely affect the healing process.

[0025] The relief incisions are designed, if possible, to prevent epithelial cells from migrating deeply into the cornea in the event of a gap. This can also be improved by aligning the incisions not, or not entirely, perpendicular to the surface. This can also be improved by aligning the incisions not, or not entirely, radially or circularly relative to the center of the cornea.

[0026] The invention is not only suitable for improving hyperopia correction. It is also applicable analogously for myopia correction using lenticule transplantation.

[0027] The invention can be used in conjunction with implants made of plastic or biomaterial but also in conjunction with transplants, in particular with transplanted lenticules.

[0028] The invention is not limited to the cut shapes presented below. As long as the cuts are consistent in terms of intended purpose, mechanism of action, and approximate location, the method for their planning, production, implementation, and the corresponding devices are also claimed. Additional cuts can also be introduced, for example, for correcting astigmatism or higher-order visual defects.

[0029] It is understood that the features mentioned above and those to be explained below can be used not only in the combinations indicated, but also in other combinations or on their own, without departing from the scope of the present invention.

[0030] The invention is explained in more detail below, for example, with reference to the accompanying drawings, which also disclose essential features of the invention. They show: Fig. 1 a schematic representation of a treatment device with a planning device for a follow-up treatment in ophthalmic surgical refractive correction, Fig. 2 a schematic representation of the effect of the laser radiation used in the treatment device of the Fig. 1 is used, Fig. 3 another schematic representation of the treatment device of the Fig. 1 regarding the introduction of laser radiation, Fig. 4 a schematic cross-sectional view through the cornea to illustrate the removal of a corneal volume in connection with an ophthalmic surgical refractive correction according to the state of the art, Fig. 5 a schematic representation of the structure of the treatment device of the Fig. 1 with particular reference to the planning facility there, Fig. 6 a schematic diagram illustrating the insertion of an inlay in connection with an ophthalmic surgical refractive correction according to the state of the art Fig. 7 a schematic diagram to illustrate the invention Fig. 8 a schematic diagram illustrating the invention in a second embodiment Fig. 9 a schematic diagram illustrating the invention in a further embodiment Fig. 10 a schematic diagram illustrating the invention in a further embodiment in connection with an astigmatism correction Fig. 11 a schematic representation of various other cutting geometries.

[0031] A treatment device for eye surgery is in Fig. 1 and provided with the general reference numeral 1. The treatment device 1 is designed for making laser incisions on an eye 2 of a patient 3. For this purpose, the treatment device 1 has a laser device 4 which emits a laser beam 6 from a laser source 5, which is directed as a focused beam 7 into the eye 2 or the cornea. The laser beam 6 is preferably a pulsed laser beam with a wavelength between 300 nanometers and 10 micrometers. Furthermore, the pulse length of the laser beam 6 is in the range between 1 femtosecond and 100 nanoseconds, with pulse repetition rates of 50 to 50,000 kilohertz and pulse energies between 0.01 microjoules and 0.01 millijoules being possible. The treatment device 1 thus creates an incision surface in the cornea of the eye 2 by deflecting the pulsed laser radiation. In the laser device 4 orA scanner 8 and a radiation intensity modulator 9 are therefore also provided for the laser source 5.

[0032] The patient 3 is positioned on a couch 10 that is adjustable in three spatial directions to align the eye 2 to match the incidence of the laser beam 6. In a preferred design, the couch 10 is motor-adjustable.

[0033] The control can be carried out in particular by a control unit 11, which fundamentally controls the operation of the treatment device 1 and is connected to the treatment device via suitable data connections, for example, connecting lines 12. Of course, this communication can also take place via other means, for example, fiber optics or radio. The control unit 11 makes the appropriate settings and time control on the treatment device 1, in particular the laser device 4, and thus performs the corresponding functions of the treatment device 1.

[0034] The treatment device 1 further comprises a fixation device 15, which fixes the cornea of the eye 2 in position relative to the laser device 4. This fixation device 15 can comprise a known contact lens 45, to which the cornea is applied by negative pressure and which imparts the desired geometric shape to the cornea. Such contact lenses are known to the person skilled in the art from the prior art, for example, from DE 102005040338 A1.

[0035] The treatment device 1 further comprises a camera (not shown here) that can capture an image of the cornea 17 through the contact lens 45. The illumination for the camera can be in both the visible and infrared ranges of light.

[0036] The control unit 11 of the treatment device 1 further comprises a planning device 16, which will be explained in more detail later.

[0037] Fig. 2 shows schematically the mode of operation of the incident laser beam 6. The laser beam 6 is focused and falls as the focused laser beam 7 into the cornea 17 of the eye 2. A schematically drawn optic 18 is provided for focusing. It causes a focus in the cornea 17 in which the laser radiation energy density is so high that, in combination with the pulse length of the pulsed laser radiation 6, a non-linear effect occurs in the cornea 17. For example, each pulse of the pulsed laser radiation 6 in the focus 19 can create an optical breakthrough in the cornea 17, which in turn Fig. 2 only schematically indicated plasma bubble is initiated. When the plasma bubble forms, the tissue layer separation covers a larger area than the focus 19, although the conditions for generating the optical breakthrough are only achieved in the focus 19. In order for each laser pulse to generate an optical breakthrough, the energy density, i.e. the fluence of the laser radiation must be above a certain, pulse length-dependent threshold value. This relationship is known to the person skilled in the art, for example, from DE 69500997 T2. Alternatively, a tissue-separating effect can also be achieved by pulsed laser radiation by emitting several laser radiation pulses in one area, with the focus spots overlapping. Several laser radiation pulses then act together to achieve a tissue-separating effect.However, the type of tissue separation used by the treatment device 1 is not further relevant for the following description; what is essential is merely that a cut is created in the cornea 17 of the eye 2.

[0038] To perform an ophthalmic refractive correction, a corneal volume is removed from an area within the cornea 17 using laser radiation 6. Tissue layers are separated there, isolating the corneal volume and then enabling its removal. To isolate the corneal volume to be removed, for example, in the case of pulsed laser radiation, the position of the focus 17 of the focused laser radiation 7 in the cornea 17 is adjusted. This is shown schematically in Fig. 3 shown. The refractive properties of the cornea 17 are specifically altered by removing the volume in order to achieve refractive correction. The volume is therefore usually lens-shaped and is referred to as a lenticule. For the present invention, however, it is sufficient to separate the tissue layers in such a way that a pocket is created to accommodate the implant.

[0039] In Fig. 3 The elements of the treatment device 1 are shown only to the extent that they are necessary for understanding the incision creation. The laser beam 6 is, as already mentioned, focused in a focus 19 in the cornea 19, and the position of the focus 19 in the cornea is adjusted so that, to create the incision, focused energy from laser radiation pulses is introduced into the tissue of the cornea 17 at different locations. The laser radiation 6 is preferably provided by the laser source 5 as pulsed radiation. The scanner 8 is constructed in the manner of Fig. 3 It has a two-part construction and consists of an xy scanner 8a, which in one variant is implemented by two essentially orthogonally deflecting galvanometer mirrors. The scanner 8a deflects the laser beam 6 coming from the laser source 5 in two dimensions, so that a deflected laser beam 20 is present after the scanner 9. The scanner 8a thus effects an adjustment of the position of the focus 19 essentially perpendicular to the main direction of incidence of the laser beam 6 in the cornea 17. To adjust the depth of field, in addition to the xy scanner 8a, the scanner 8 also contains a z scanner 8b, which is designed, for example, as an adjustable telescope. The z scanner 8b ensures that the z position of the focus 19, i.e. its position on the optical axis of incidence, is changed. The z scanner 8b can be arranged upstream or downstream of the xy scanner 8a.

[0040] For the functional principle of the treatment device 1, the assignment of the individual coordinates to the spatial directions is not essential, nor is it important that the scanner 8a deflects around mutually perpendicular axes. Rather, any scanner can be used that is capable of adjusting the focus 19 in a plane in which the axis of incidence of the optical radiation does not lie. Furthermore, any non-Cartesian coordinate system can be used for deflecting or controlling the position of the focus 19. Examples of this are spherical coordinates or cylindrical coordinates. The position of the focus 19 is controlled by means of the scanners 8a, 8b under the control of the control unit 11, which makes corresponding settings on the laser source 5, the (in Fig. 3 not shown) modulator 9 and the scanner 8. The control unit 11 ensures suitable operation of the laser source 5 as well as the three-dimensional focus adjustment described here as an example, so that ultimately a cutting surface is formed that isolates a specific corneal volume that is to be removed for refraction correction.

[0041] The control device 11 operates according to predefined control data, which, for example, are specified as target points for the focus adjustment in the laser device 4 described here only as an example. The control data are generally summarized in a control data set. This provides geometric specifications for the cutting surface to be formed, for example, the coordinates of the target points as a template. In this embodiment, the control data set then also contains specific position values for the focus position adjustment mechanism, e.g., for the scanner 8.

[0042] The generation of the cutting surface with the treatment device 1 is shown as an example in Fig. 4 shown. A corneal volume 21 in the cornea 17 is isolated by adjusting the focus 19, in which the focused beam 7 is bundled. For this purpose, cutting surfaces are formed, which are designed here as an anterior flap cutting surface 22 and a posterior lenticule cutting surface 23. These terms are to be understood merely as examples and are intended to establish a reference to the conventional LASIK or lenticule extraction procedure (SMILE), for which the treatment device 1, as already described, is also designed. The only essential point here is that the cutting surfaces 22 and 23, as well as unspecified edge cuts that join the cutting surfaces 22 and 23 at their edges, isolate the corneal volume 21. Through an opening incision 24, a corneal lamella that limits the corneal volume 21 anteriorly can be folded down so that the corneal volume 21 can be removed.This corneal lamella defined by the anterior incision has a constant thickness in the preferred embodiment, but can also have an inhomogeneous thickness, in particular a radius-dependent thickness.

[0043] Alternatively, the SMILE procedure can be used, in which the corneal volume 21 is removed through a small incision, as described in DE 10 2007 019813 A1. An implant (inlay) can then be inserted into the pocket created in this or another manner.

[0044] Fig. 5 shows a schematic view of the treatment device 1, and the significance of the planning device 16 will be explained in more detail based on this. The treatment device 1 in this variant has at least two devices or modules. The already described laser device 4 emits the laser beam 6 onto the eye 2. The operation of the laser device 4 is, as already described, fully automatic by the control unit 11, i.e. the laser device 4 starts the generation and deflection of the laser beam 6 upon a corresponding start signal and thereby creates cutting surfaces that are constructed in the manner described. The laser device 5 receives the control signals required for operation from the control unit 11, to which corresponding control data was previously provided. This is done by means of the planning device 16, which in Fig. 5 is shown merely as an example as a component of the control unit 11. Of course, the planning device 16 can also be designed independently and communicate with the control unit 11 via wired or wireless communication. In this case, it is only essential that a corresponding data transmission channel is provided between the planning device 16 and the control unit 11.

[0045] The planning device 16 generates a control data set that is made available to the control unit 11 for performing the ophthalmic refractive correction. The planning device uses measurement data about the cornea of the eye. In the embodiment described here, this data originates from a measuring device 28 that previously measured the eye 2 of the patient 2. Of course, the measuring device 28 can be configured in any desired manner and transmit the corresponding data to the interface 29 of the planning device 16.

[0046] The planning device now supports the operator of the treatment device 1 in determining the incision surface for isolating the corneal volume 21 or creating a pocket for an implant, or in creating the relief incisions according to the invention. This can extend to fully automatic determination of the incisions, which can be achieved, for example, by the planning device 16 determining the corneal volume 21 to be removed from the measurement data, defining its boundary surfaces as incision surfaces, and generating corresponding control data for the control unit 11. At the other end of the automation level, the planning device 16 can provide input options where a user enters the incisions in the form of geometric or optical parameters (refractive powers or changes in refractive power) or mechanical parameters (elasticity), or where these are automatically derived from diagnostic data.Intermediate stages provide suggestions for the cuts, which the planning device 16 automatically generates and which can then be modified by an operator. In principle, all the concepts already explained in the more general description section above can be applied here in the planning device 16.

[0047] In order to carry out a treatment, the planning device 16 generates control data for the cut generation, which are then used in the treatment device 1.

[0048] Fig. 6a shows a schematic representation of a cutting geometry for a pocket according to the state of the art to illustrate the geometric relationships in cross-section. The cornea 17 has a pocket incision P with an opening incision O under the cap C. An inlay L was inserted through the opening incision O. The inlay L thereby changes the geometry of the cornea 17 by deforming the front surface V of the cornea. A possible explanation for the observed deviations between the target and actual refraction after implantation of an inlay could be that the back surface of the cornea also deforms from H to H', but the front surface of the cornea reacts mechanically and only has a deformation V' that deviates from the target deformation V, thus creating a refractive state other than the desired one. Fig. 6b shows a top view of the Fig. 6a depicted cornea.

[0049] To counteract this undesirable deviation from the target geometry, additional relief incisions are made in the cornea above the Cap C.

[0050] The cutting geometries according to the invention are described in more detail below.

[0051] Fig. 7a shows a schematic representation of a first incision geometry according to the invention in cross-section. The relief cuts T and U are designed as circular arc segments that run symmetrically around the optically effective zone of the eye. Fig. 7b shows a top view of the Fig. 7a depicted cornea.

[0052] Fig. 8a shows a schematic representation of a second incision geometry according to the invention in cross-section. The relief incisions T and U are designed as complete circular arcs that extend outside the optically effective zone of the eye. The relief incisions cause a more effective deformation of the anterior corneal surface and reduce the deformation of the posterior corneal surface. Fig. 8b shows a top view of the Fig. 8a depicted cornea.

[0053] Fig. 9a shows a schematic representation of another cutting geometry according to the invention in cross-section. The relief cuts T are designed as oblique-radial cuts. This cutting variant can promote the intended fabric expansion in the cap. Fig. 9b shows a top view of the Fig. 9a depicted cornea.

[0054] Fig. 10a shows a schematic representation of another cutting geometry as a modification of the one in Fig. 8 shown geometry in cross-section. Here, astigmatism is corrected by a circular arc cut U that is not symmetrical to the eye axis. Fig. 10b shows a top view of the Fig. 10a depicted cornea

[0055] In Fig. 11 Further possible incision geometries for the relief incisions T are shown. Depending on the type and extent of the desired tissue stretching, these incision variants enable better predictability of the outcome of the procedure and accelerated healing.

[0056] In Fig. 11c is the astigmatism correction from Fig. 10 in connection with the cutting design of circular arcs according to Fig. 8 shown.

[0057] As can be seen from the figures, the relief incisions T and U do not extend to the anterior surface of the cornea to avoid the risk of tearing or gaping. To ensure mechanical stability, they also do not extend to the inlay L. For a given thickness d (between 140 µm and 200 µm) of the cap C, it is usually advantageous for the incisions to have a maximum depth of 0.8 xd. However, in special cases, it may also be advantageous for relief incisions T and U to extend to the inlay L.

[0058] In addition, it should be noted that the treatment device 1 or the planning device 16, of course, also concretely implements the method explained in general terms above.

[0059] A further embodiment of the planning device is in the form of a computer program or a corresponding data carrier with a computer program, which implements the planning device on a corresponding computer, so that the input of the measurement data to the computer takes place via suitable data transmission means and the control data are transmitted from this computer to the control unit 11, for which purpose data transmission means known to the person skilled in the art can be used.

Claims

1. Planning device (16) for generating control data for a treatment apparatus (1) for eye surgery which generates at least one incision in the cornea (17) by means of a laser device (4), wherein the planning device (16) comprises calculation means for defining at least one corneal relief incision (T, U), wherein the calculation means define the at least one corneal relief incision based on the data of a refractive correction, and generate a control data record for controlling the laser device (4) for the corneal relief incisions (T, U), wherein the calculation means determine the at least one corneal relief incision (T, U) in such a way that refractive errors present following the insertion of an implant (L) into a pocket in the cornea (17), with an incision geometry of the pocket comprising a pocket incision (P) under a cap (C) of thickness d and an opening incision (O), are countervailed, characterized in that the at least one corneal relief incision (T, U) extends in the cap (C), does not reach the anterior corneal surface and does not reach deeper than the pocket incision (P) and extends outside the optically effective zone.

2. Planning device (16) according to Claim 1, wherein the at least one corneal relief incision (T, U) has a maximum extension in depth of 0.8 x d.

3. Planning device (16) according to Claim 1 or 2, wherein the at least one corneal relief incision (T, U) is embodied as a circular arc, as circular arc segments, as radially extending incisions or as obliquely-radially extending incisions.

4. Treatment apparatus (1) for eye surgery, which - comprises a laser device (4) which according to control data generates at least one cut surface in the cornea (17) by means of laser radiation, and - comprises a planning device (16) for generating the control data, wherein the planning device (16) comprises calculation means for defining at least one corneal relief incision (T, U), wherein the calculation means define the at least one corneal relief incision (T, U) based on the data of a refractive correction, and generate a control data record for controlling the laser device (4) for the at least one corneal relief incision (T, U), wherein the planning device (16) determines the at least one corneal relief incision (T, U) in such a way that refractive errors present following the insertion of an implant (L) into a pocket in the cornea (17), with an incision geometry of the pocket comprising a pocket incision (P) under a cap (C) of thickness d and an opening incision (O), are countervailed, characterized in that the at least one corneal relief incision (T, U) extends in the cap (C), does not reach the anterior corneal surface and does not reach deeper than the pocket incision (P) and extends outside the optically effective zone.

5. Treatment device (1) according to Claim 4, wherein the at least one corneal relief incision (T, U) has a maximum extension in depth of 0.8 x d.

6. Treatment device (1) according to Claim 4 or 5, wherein the at least one corneal relief incision (T, U) is embodied as a circular arc, as circular arc segments, as radially extending incisions or as obliquely-radially extending incisions.

7. Method for generating control data for a treatment apparatus (1) for eye surgery which generates at least one incision in the cornea (17) by means of a laser device, wherein the method is characterized by the following steps: providing corneal data based on data of a refractive correction, defining at least one corneal relief incision (T, U) and generating a control data record for the at least one corneal relief incision (T, U) for the purpose of controlling the laser device (4), wherein the at least one corneal relief incision (T, U) is determined in such a way that refractive errors present following the insertion of an implant (L) into a pocket in the cornea (17), with an incision geometry of the pocket comprising a pocket incision (P) under a cap (C) of thickness d and an opening incision (O), are countervailed, characterized in that the at least one corneal relief incision (T, U) extends in the cap (C), does not reach the anterior corneal surface and does not reach deeper than the pocket incision (P) and extends outside the optically effective zone.

8. Method according to Claim 7, wherein the at least one corneal relief incision (T, U) has a maximum extension in depth of 0.8 x d.

9. Method according to Claim 7 or 8, wherein the at least one corneal relief incision (T, U) is embodied as a circular arc, as circular arc segments, as radially extending incisions or as obliquely-radially extending incisions.

10. Computer program product having program code which upon execution on a computer carries out the method according to any of Claims 7 to 9.

11. Data medium having a computer program product according to Claim 10.