Method for providing control data for an ophthalmic surgical laser of a treatment device, taking into account the dehydration time

Abstract

Method for providing control data for an ophthalmic surgical laser (12) of a treatment device (10) for the removal of tissue (14) from a human or animal cornea, taking into account a dehydration time, wherein the method comprises the following steps performed by a control device (18): - Determining (S1) the expected dehydration time of the cornea, wherein the dehydration time is estimated as a function of a planned treatment or partial treatment with the treatment device (10); - Calculating (S2) a dehydration laser pulse efficiency expected due to corneal dehydration effects, wherein the dehydration laser pulse efficiency is calculated from a predetermined initial laser pulse efficiency assumed without dehydration effects using a corneal dehydration model, at least as a function of the determined dehydration time;- Determining (S3) a laser pulse pattern for tissue removal (14) using the calculated dehydration laser pulse efficiency; - Providing (S4) control data for controlling the ophthalmic surgical laser (12) using the laser pulse pattern for tissue removal (14).

Description

[0001] The present invention relates to a method for providing control data for an ophthalmic surgical laser of a treatment device for the removal of tissue from a human or animal cornea. The invention further relates to a treatment device comprising at least one ophthalmic surgical laser and at least one control unit for carrying out the method, a computer program, and a computer-readable medium.

[0002] Treatment devices and methods for controlling ophthalmic lasers to correct refractive errors and / or pathologically or abnormally altered areas of the cornea are known in the prior art. For example, a pulsed laser and a beam focusing device can be configured such that laser pulses cause photodisruption and / or photoablation at a focus located within the organic tissue in order to remove tissue, in particular a tissue lenticel, from the cornea. For tissue removal, it is necessary to provide suitable control data that specifies the positions on the cornea where laser pulses must be applied to achieve the desired treatment outcome, with the number and position of the laser pulses in the cornea depending on the efficiency of the laser pulses.Since the eye must remain open throughout the entire treatment, it can dry out during the procedure. This means that dehydration effects can occur in the cornea, which can alter the efficiency of the laser pulses and thus make the control data regarding the predetermined positions of the laser pulses in the cornea inaccurate. These dehydration effects are currently disregarded, which can lead to inaccuracies in the treatment with the device.

[0003] The invention is therefore based on the objective of providing improved control data for controlling an ophthalmic surgical laser.

[0004] This problem is solved by the inventive method, the inventive devices, the inventive computer program, and the inventive computer-readable medium. Advantageous embodiments with expedient further developments of the invention are specified in the respective dependent claims, wherein advantageous embodiments of the method are to be regarded as advantageous embodiments of the treatment device, the control device, the computer program, and the computer-readable medium, and vice versa.

[0005] A first aspect of the invention relates to a method for providing control data to an ophthalmic surgical laser of a treatment device for the removal of tissue from a human or animal cornea, wherein the method comprises the following steps performed by a control device. A control device is understood to be a device, a device component, or a group of devices configured to receive and evaluate signals and to provide, for example, generate, control data. The control device can be configured, for example, as a control chip, computer program, computer program product, or control unit. The control device determines the expected dehydration time of the cornea, the dehydration time being estimated as a function of a planned treatment or partial treatment with the treatment device.Furthermore, a dehydration laser pulse efficiency is calculated, which is expected due to corneal dehydration effects. Starting from a predetermined initial laser pulse efficiency (assumed without dehydration effects), this efficiency is calculated using a corneal dehydration model, at least as a function of the determined dehydration time. Finally, a laser pulse pattern for tissue removal is determined using the calculated dehydration laser pulse efficiency, and control data is provided for controlling the ophthalmic surgical laser, which uses this laser pulse pattern to remove the tissue.

[0006] In other words, the expected dehydration time is first estimated based on the planned treatment or partial treatment of the cornea. Dehydration time refers to the period during which the eye must remain open due to the treatment, thus allowing the cornea to dry out. For example, the dehydration time could be the time between the last rehydration of the eye, particularly through blinking, and the end of the treatment or partial treatment. This dehydration time can be estimated statistically, for instance, using predefined treatment times for different conditions. Alternatively, a commonly used pulse pattern and its duration can be used to estimate the dehydration time.This dehydration time can then be used to calculate how the initial laser pulse efficiency, assumed without dehydration effects, changes after the dehydration period—that is, how the laser pulses act on a dehydrated cornea. In other words, the laser pulse efficiency changes after the dehydration period to the dehydration laser pulse efficiency. Specifically, depending on the amount of water lost from the cornea, more or less tissue can be removed by a single laser pulse, which can change the efficiency of a laser pulse over time. Furthermore, in a dehydrated eye, the cornea can become thinner because the intermediate layers of the cornea no longer contain as much water.

[0007] The dehydration laser pulse efficiency can preferably be calculated using a corneal dehydration model, which can specify how a given indicative laser pulse efficiency can decrease or increase over time. The dehydration model can thus mathematically describe how the laser pulse efficiency changes over time, particularly after the dehydration period, and can preferably be derived from empirically obtained measurement data. Once the dehydration laser pulse efficiency, determined as a function of the dehydration period, has been calculated, a laser pulse pattern for tissue removal can be determined. For example, the corneal dehydration model can determine that the laser pulses are more effective in a dehydrated cornea.This could, for example, result in the use of a laser pulse pattern that requires fewer laser pulses to remove the tissue.

[0008] Finally, control data for the ophthalmic surgical laser can be provided, containing the determined laser pulse pattern for tissue removal. The invention offers the advantage that corneal dehydration is taken into account when providing the control data, thereby enabling more precise and less variable ablations. Overall, improved control data can be provided, consequently enhancing treatment with an ophthalmic surgical laser or treatment device.

[0009] The invention also includes embodiments that offer additional advantages.

[0010] One embodiment provides that the expected dehydration time is determined by calculating the time from a predetermined reference point, at which the initial laser pulse efficiency is known, until the end of the treatment or partial treatment with the treatment device. In other words, the dehydration time is determined as the total time from a reference point until the end of the treatment or partial treatment. Preferably, the initial laser pulse efficiency, i.e., how the laser pulses affect the cornea, can be known at the reference point. The initial laser pulse efficiency can be known, for example, for a cornea in its normal state, meaning in a non-dehydrated state.Using the dehydration model, the dehydration laser pulse efficiency can be calculated based on the initial laser pulse efficiency and the dehydration time, where the total treatment time is assumed to be the dehydration time. Thus, the laser pulse efficiency (dehydration laser pulse efficiency) can be determined as it would be for a dehydrated cornea at the end of the treatment. This determined dehydration laser pulse efficiency can then be assumed to apply to the entire treatment or partial treatment, thereby simplifying the determination of the laser pulse pattern. The duration of the treatment or partial treatment can be predetermined based on experience or determined statistically by the control unit. Preferably, one or more similar treatments or partial treatments can have been performed previously, and an average duration can be determined from these, for example, by the control unit.

[0011] In a further embodiment, the expected dehydration time is determined by measuring the time from a predetermined reference point, at which the initial laser pulse efficiency is known, until halfway through the treatment or partial treatment with the treatment device. In other words, as in the previous embodiment, a reference point, at which the initial laser pulse efficiency is known, can again be used as the starting point, but in this embodiment, the dehydration time is only determined until halfway through the treatment or partial treatment. Halfway through the treatment time or the time of the partial treatment can, for example, be estimated from experience, particularly from previous treatments with the treatment device.The resulting dehydration laser pulse efficiency, which can be assumed for the entire treatment, represents the laser pulse efficiency as it would be after half or part of the treatment. This design offers the advantage of achieving a compromise between treatment without dehydration correction and treatment with maximum dehydration correction, as would be the case after the entire dehydration period. The dehydration laser pulse efficiency is thus averaged, which is easy to calculate and still compensates for dehydration effects.

[0012] In a particularly advantageous embodiment, a plurality of laser pulses are delivered into the cornea during treatment or partial treatment with the treatment device. The anticipated dehydration time for each laser pulse is estimated separately. This dehydration time is determined from a predetermined reference time, at which the initial laser pulse efficiency is known, until the respective laser pulse. Furthermore, the dehydration laser point efficiency is calculated for the respective dehydration time of each laser pulse, and the laser pulse pattern is determined as a function of the respective calculated dehydration laser pulse efficiency. In other words, the time elapsed from the predetermined reference time until each laser pulse during treatment or partial treatment is determined, thus ensuring that each laser pulse has its own anticipated dehydration time.Thus, for each laser pulse and the determined dehydration time, a separate dehydration laser pulse efficiency can be calculated. This offers the advantage that the laser pulse pattern can be determined even more precisely, since the dehydration laser pulse efficiency is known for each individual laser pulse.

[0013] Preferably, a portion of the dehydration time is predetermined, from the insertion of an eyelid retractor until the first laser pulse. An eyelid retractor is typically used during treatment with the device to keep the eye open, thus enabling continuous irradiation with the ophthalmic laser. The eyelid retractor prevents eyelid closure. However, corneal dehydration can begin as soon as the retractor is inserted, since corneal rehydration is no longer possible due to eyelid closure. The dehydration time can therefore consist of an irradiation time portion during which laser pulses are delivered to the cornea, and a time portion elapsed from the insertion of the eyelid retractor until the first laser pulse is delivered to the cornea. This latter time portion can be predetermined, for example, based on empirical data.For example, it may be known that after insertion of the eyelid speculum, five or ten minutes elapse before the ophthalmic laser is adjusted to deliver the first laser pulse to the cornea. This time can be added to the dehydration time as a constant. In particular, the time of insertion of the eyelid speculum can also be used as a reference point, at which the initial laser pulse efficiency is known. Specifying the time between insertion of the eyelid speculum and the first laser pulse offers the advantage of a more precise determination of the dehydration time.

[0014] In a further embodiment, the corneal dehydration model is designed to describe changes in the cornea's water content and thickness over time, particularly during the dehydration period. In other words, the laser pulse efficiency during ophthalmic laser treatment can change because, on the one hand, the cornea's water content decreases during dehydration, and on the other hand, the cornea's thickness can decrease as tissue layers shrink due to dehydration. Consequently, a laser pulse can remove more tissue after dehydration than before. These effects can be incorporated into the dehydration model, allowing for the determination of improved dehydration laser pulse efficiency and thus leading to an improved laser pulse pattern.

[0015] In a further advantageous embodiment, the humidity in the environment of the treatment device is also determined, and this determined humidity is additionally used in the corneal dehydration model to calculate the dehydration laser pulse efficiency. In other words, corneal dehydration can depend on the humidity of the air in the environment of the treatment device. Therefore, it is provided to determine the humidity and additionally consider it in the dehydration model. This embodiment offers the advantage that the dehydration model can be improved, thus enabling the determination of an improved dehydration laser pulse efficiency.

[0016] Preferably, the dehydration laser pulse efficiency is determined by the corneal dehydration model according to the formula: Eƒƒ(t0+Δt)=Eƒƒ(t0)*(1−Henv−ΔH(t0)e−Δtτh1−Henv−ΔH(t0))2 is calculated where Eff (t0) is the given initial laser pulse efficiency, H env where AH(t0) is the humidity of an environment surrounding the treatment device, AH(t0) is the difference between a predetermined corneal moisture level and the humidity, and where Δt is the dehydration time in the exponent of the exponential function and τ is a predetermined dehydration time constant. h The dehydration model with the aforementioned formula can, for example, be stored in the control unit, where an algorithm can insert the variables and automatically calculate the dehydration laser pulse efficiency. Using this dehydration laser pulse efficiency, the laser pulse pattern for treating or partially treating the cornea can then be determined using known methods.

[0017] A second aspect of the present invention relates to a control device configured to perform one of the methods described above. This results in the advantages listed above. The control device can, for example, be configured as a control chip, control unit, or user program ("app"). The control device can preferably include a processor and / or a data storage device. A processor is understood to be a device or device component for electronic data processing. The processor can, for example, include at least one microcontroller and / or at least one microprocessor. The optional data storage device can preferably contain program code for carrying out the method according to the invention.The program code can then be designed, when executed by the processor, to cause the control unit to carry out one of the embodiments of one or both of the methods of the invention described above.

[0018] A third aspect of the present invention relates to a treatment device comprising at least one ophthalmic surgical laser for the separation of tissue predefined by the control data, in particular a corneal volume with predefined interfaces of a human or animal eye, by means of photodisruption and / or photoablation, and at least one control unit for the laser(s) configured to perform the steps of the method according to the first aspect of the invention. The treatment device according to the invention makes it possible to reliably reduce or even avoid the disadvantages that occur when using conventional ablative treatment devices.

[0019] In a further advantageous embodiment of the treatment device according to the invention, the laser can be suitable for emitting laser pulses in a wavelength range between 300 nm and 1400 nm, preferably between 700 nm and 1200 nm, with a pulse duration between 1 fs and 1 ns, preferably between 10 fs and 10 ps, ​​and a repetition frequency greater than 10 kilohertz (kHz), preferably between 100 kHz and 100 megahertz (MHz). Such a femtosecond laser is particularly well suited for removing tissue within the cornea. The use of photodisruptive and / or photoablative lasers in the method according to the invention also has the advantage that the irradiation of the cornea does not have to take place in a wavelength range below 300 nm. This range is referred to in laser technology as "deep ultraviolet".This advantageously prevents unintentional damage to the cornea caused by these very short-wavelength and high-energy beams. Photodisruptive lasers of the type used here typically deliver pulsed laser radiation with a pulse duration between 1 fs and 1 ns into the corneal tissue. This allows the power density of the respective laser pulse, necessary for optical breakthrough, to be spatially tightly limited, thus enabling high cutting accuracy in the generation of the interfaces. The wavelength range between 700 nm and 780 nm can also be selected.

[0020] In further advantageous embodiments of the treatment device according to the invention, the control unit can have at least one storage device for at least temporarily storing at least one control data set, wherein the control data set(s) comprise control data for positioning and / or focusing individual laser pulses in the cornea; and can have at least one beam device for beam guidance and / or beam shaping and / or beam deflection and / or beam focusing of a laser beam. The aforementioned control data set comprises the control data determined in the method for tissue removal.

[0021] Further features and their advantages can be found in the descriptions of the first aspect of the invention, whereby advantageous embodiments of each aspect of the invention are to be regarded as advantageous embodiments of the other aspect of the invention.

[0022] A fourth aspect of the invention relates to a computer program comprising commands that cause the treatment device according to the fourth aspect of the invention to perform the process steps according to the first aspect of the invention and / or the process steps according to the second aspect of the invention.

[0023] A fifth aspect of the invention relates to a computer-readable medium on which the computer program according to the fourth aspect of the invention is stored. Further features and their advantages can be found in the descriptions of the first to fourth aspects of the invention, whereby advantageous embodiments of each aspect of the invention are to be regarded as advantageous embodiments of the other aspects of the invention.

[0024] Further features of the invention are evident from the claims, the figures, and the description of the figures. The features and combinations of features mentioned above in the description, as well as those subsequently mentioned in the description of the figures and / or shown in the figures alone, are not only usable in the combinations specified, but also in other combinations without departing from the scope of the invention. Thus, embodiments that are not explicitly shown and explained in the figures, but which can be derived and generated from the explained embodiments by separate combinations of features, are also to be considered as encompassed and disclosed by the invention. Embodiments and combinations of features that do not exhibit all the features of an originally formulated independent claim are also to be considered disclosed.Furthermore, embodiments and combinations of features, in particular those set out above, are to be considered disclosed which go beyond or deviate from the combinations of features set out in the cross-references of the claims. This shows: Fig. 1 a schematic representation of a treatment device according to the invention in an exemplary embodiment; Fig. 2 a schematic process diagram according to an exemplary embodiment;

[0025] In the figures, identical or functionally equivalent elements are provided with the same reference symbols.

[0026] The Fig. Figure 1 shows a schematic representation of a treatment device 10 with an ophthalmic surgical laser 12 for removing tissue 14 from the cornea of ​​a human or animal eye 16 by means of photodisruption and / or photoablation. The tissue 14 can, for example, be a lenticule or a volumetric body that can be removed from the cornea of ​​the eye 16 with the ophthalmic surgical laser 12 to correct a refractive error. A laser pulse pattern for removing the tissue 14 can be provided by a control device 18, in particular in the form of control data, so that the laser 12 emits pulsed laser pulses into the cornea in a pattern predefined by the control data to remove the tissue 14. Alternatively, the control device 18 can be an external control device 18 with respect to the treatment device 10.

[0027] Furthermore, the Fig. 1, that the laser beam 20 generated by the laser 12 can be deflected towards the eye 16 by means of a beam deflection device 22, namely a beam deflection device such as a rotary scanner, in order to remove the tissue 14. The beam deflection device 22 can also be controlled by the control device 18 to remove the tissue 14.

[0028] The laser 12 shown is preferably a photodisruptive and / or photoablative laser configured to emit laser pulses in a wavelength range between 300 nanometers and 1400 nanometers, preferably between 700 nanometers and 1200 nanometers, with a pulse duration between 1 femtosecond and 1 nanosecond, preferably between 10 femtoseconds and 10 picoseconds, and a repetition frequency greater than 10 kilohertz, preferably between 100 kilohertz and 100 megahertz. The control device 18 optionally also includes a storage device (not shown) for at least temporarily storing at least one control data set, wherein the control data set(s) comprise control data for positioning and / or focusing individual laser pulses in the cornea 16.

[0029] To suppress eyelid closure during treatment with the treatment device 10, an eyelid restrictor 24 can also be provided, which keeps the eye 16 open during the treatment. A disadvantage of this is that the eye 16 is no longer moistened by the natural eyelid closure and dries out or becomes dehydrated. Due to dehydration of the eye 16, laser pulses from the laser 12 may therefore have a different efficiency in removing tissue 14 than originally planned. For example, the cornea of ​​the eye 16 may contract and change thickness due to dehydration. This could result in more tissue being removed during the treatment or partial treatment than originally intended.

[0030] To avoid this, the following can be done in Fig.The schematic methods shown in Figure 2 for providing control data to the ophthalmic surgical laser 12 via the control unit 18 are performed. In step S1, an estimated corneal dehydration time can be determined, during which the cornea will dehydrate due to the planned treatment or partial treatment. This can be done, for example, using empirical data on the average duration of a treatment with the treatment device 10, particularly a treatment tailored to the patient. For instance, the estimated dehydration time can be calculated from a predetermined reference time to the end of the treatment or partial treatment, preferably with the initial laser pulse efficiency being known at the predetermined reference time.

[0031] The initial laser pulse efficiency can be the efficiency of the laser that is normally assumed for a non-dehydrated eye. Alternatively, the expected dehydration time can also be determined from the predetermined reference time until halfway through the treatment or partial treatment, which represents a compromise between dehydration correction after the entire treatment time and the dehydration state at the reference time. Particularly preferably, the dehydration time can also be determined as the time from the predetermined reference time, at which the initial laser pulse efficiency is known, until each planned laser pulse of the ophthalmic surgical laser 12. Thus, a separate dehydration time can be determined for each laser pulse.

[0032] The reference point can be, for example, the activation of the eyelid restrictor 24, after which the eyelid closure reflex is no longer possible. In particular, a time fraction elapsed between the activation of the eyelid restrictor 24 and the first laser pulse delivered to the eye 16 can also be added as a constant for determining the dehydration time. This time fraction can be derived from empirical data on how long it takes from the activation of the eyelid restrictor 24 until the first laser pulse is delivered to the eye 16.

[0033] In step S2, a dehydration laser pulse efficiency can then be calculated, which is expected after the previously determined dehydration time, whereby, starting from the given initial laser pulse efficiency, a dehydration model is used and, depending on the dehydration time, the dehydration laser pulse efficiency after the expected dehydration time is calculated.

[0034] Preferably, the humidity of the environment surrounding the treatment device 10 can also be determined to ascertain the efficiency of the dehydration laser pulse, and this humidity parameter can be added to the dehydration model. The dehydration model can be a mathematical-physical formula that calculates how the efficiency of the laser pulse changes over the dehydration period, i.e., due to the drying of the cornea. The dehydration model can preferably take into account the changing moisture of the eye and, additionally, the effect of corneal thinning 16 over time due to the drying process. Preferably, this results in a corneal dehydration model by which the efficiency of the dehydration laser pulse can be calculated according to the formula. Eƒƒ(t0+Δt)=Eƒƒ(t0)*(1−Henv−ΔH(t0)e−Δtτh1−Henv−ΔH(t0))2, where Eff (to) is the predetermined initial laser pulse efficiency and H env The previously determined humidity in the environment of the treatment device is the term ΔH(to). The term ΔH(to) is a difference between a predetermined corneal moisture and the humidity, where the predetermined corneal moisture can be known from standard values ​​for a non-dehydrated eye. In the exponent of the exponential function e, Δt is the dehydration time and τ is a predetermined dehydration time constant. h The dehydration time constant τ is given. h can be predetermined, for example, from measurements, where the dehydration time constant indicates a relaxation time for which the moisture state of the eye 16 has dropped to 1 / e of its original value.

[0035] Once the dehydration laser pulse efficiency has been determined, a new laser pulse pattern for the treatment or partial treatment to remove tissue 14 can be determined in step S3, adopting the updated laser pulse efficiency (dehydration laser pulse efficiency). Since the laser pulse efficiency can increase due to dehydration, it may be necessary, for example, to deliver fewer laser pulses to the same area in the eye 16 to achieve the same effect. Thus, the laser pulses can be delivered to the eye 16 in a coarser pattern to remove tissue 14. The determination of the laser pulse pattern can be carried out using known methods.

[0036] Finally, in step S4, control data for controlling the ophthalmic surgical laser 12 can be provided by the control unit 18, which uses the laser pulse pattern for tissue removal. Thus, the dehydration of the eye 16 over time, particularly triggered by the eyelid retractor 24, can be taken into account during treatment with the treatment device 10, leading to improved treatment.

[0037] Overall, the examples show how the invention can take into account changes in ablation efficiency due to hydration changes during refractive corneal surgery.

Claims

[1] Method for providing control data for an ophthalmic surgical laser (12) of a treatment device (10) for the removal of tissue (14) from a human or animal cornea, the method comprising the following steps performed by a control device (18): - Determining (S1) an expected dehydration time of the cornea, in which the cornea dehydrates, wherein the dehydration time is estimated depending on a planned treatment or partial treatment with the treatment device (10); - Calculating (S2) a dehydration laser pulse efficiency expected due to corneal dehydration effects, wherein the dehydration laser pulse efficiency is calculated from a given initial laser pulse efficiency assumed without dehydration effects using a corneal dehydration model at least as a function of the determined dehydration time; - Determining (S3) a laser pulse pattern for tissue removal (14) using the calculated dehydration laser pulse efficiency; - Providing (S4) control data to control the ophthalmic surgical laser (12) which uses the laser pulse pattern to remove tissue (14). [2] Method according to claim 1, characterized by , that the expected dehydration time is determined by means of a time from a predetermined reference time, at which the initial laser pulse efficiency is known, until the end of the treatment or partial treatment with the treatment device (10). [3] Method according to claim 1, characterized by , that the expected dehydration time is determined by means of a time from a predetermined reference time, at which the initial laser pulse efficiency is known, until half of the treatment or partial treatment with the treatment device (10). [4] Method according to claim 1, characterized by , that During treatment or partial treatment with the treatment device (10), a plurality of laser pulses are delivered into the cornea, with the expected dehydration time being estimated separately for each laser pulse. wherein the respective dehydration time is based on a predetermined reference time, where the initial laser pulse efficiency is known, up to the respective laser pulse is determined, furthermore the dehydration laser pulse efficiency is calculated for the respective dehydration time of the respective laser pulse and the laser pulse pattern is determined as a function of the respective calculated dehydration laser pulse efficiency. [5] Method according to any one of the preceding claims, characterized by , that a time fraction of the dehydration time is specified from the insertion of a lid specifier (24) until a first laser pulse. [6] Method according to any one of the preceding claims, characterized by , that the corneal dehydration model describes a change in the water content of the cornea and a change in the thickness of the cornea over time, especially over the dehydration time. [7] Method according to any one of the preceding claims, characterized by , furthermore, that the humidity of an environment of the treatment device (10) is determined, wherein the determined humidity is additionally used in the corneal dehydration model to calculate the dehydration laser pulse efficiency. [8] Method according to any one of the preceding claims, characterized by , that the dehydration laser pulse efficiency is determined by the corneal dehydration model according to the formula: Eƒƒ(t0+Δt)=Eƒƒ(t0)*(1−Henv−ΔH(t0)e−Δtτh1−Henv−ΔH(t0))2 is calculated where Eff(t0) is the given initial laser pulse efficiency, H envwhere is the humidity of an environment of the treatment device, ΔH(t0) is the difference between a predetermined corneal moisture and the humidity, and where e is the dehydration time with Δt and τ is a predetermined dehydration time constant in the exponent of the exponential function. h is specified. [9] Control device (18) configured to perform a procedure according to any of the preceding claims. [10] Treatment device (10) comprising at least one ophthalmic surgical laser (12) for the removal of tissue (14) of a human or animal eye (16), in particular a lenticule, by means of photodisruption and / or photoablation and at least one control device (18) according to claim 9. [11] Treatment device (10) according to claim 10, characterized by, that the laser (12) is configured to emit laser pulses in a wavelength range between 300 nm and 1400 nm, preferably between 700 nm and 1200 nm, with a respective pulse duration between 1 fs and 1 ns, preferably between 10 fs and 10 ps, ​​and a repetition frequency greater than 10 kHz, preferably between 100 kHz and 100 MHz. [12] Treatment device (10) according to one of claims 10 or 11, characterized by that the control unit - comprising at least one storage device for at least temporary storage of at least one control data set, wherein the control data set(s) comprise control data for positioning and / or focusing individual laser pulses in the cornea; and - comprising at least one beam device (22) for beam guidance and / or beam shaping and / or beam deflection and / or beam focusing of a laser beam of the laser. [13] Computer program comprising commands that cause the treatment device according to one of claims 10 to 12 to perform a method according to one of claims 1 to 8. [14] Computer-readable medium on which the computer program according to claim 13 is stored.

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