Apparatus and method for determining position of subject of interest within eye of patient and ophthalmic instrument

Abstract

The invention relates to a device for determining the position of a subject of interest in an eye of a patient, in particular in the vitreous body of the eye, having means for generating at least one beam path and a reference plane opposite the subject of interest, the device is arranged to determine, at a reference plane, an object distance between the reference plane and an object of interest.

Description

[0001] The invention relates to a device for determining the position of an object of interest within an eye of a patient, in particular within the vitreous body of the eye.

[0002] The invention further relates to an ophthalmic instrument for treating an eye of a patient, having an ophthalmic microscope.

[0003] The invention further relates to a method for determining the position of an object of interest in an eye of a patient, in particular in the vitreous body of the eye.

[0004] Different ophthalmic instruments for performing various eye treatments on patients are known from the prior art, such as ophthalmic microscopes for observing the human eye. Such microscopes consist of a number of optical components. The focal plane of the microscope is located at the focal length of the objective lens. Objects located at the focal plane will appear to be in focus to the doctor. Doctors use microscopes to observe anatomical structures in the patient's eye. Certain structures in the eye are easy to locate and focus on, for example, the iris is located at the front of the eye, is a mainly flat surface, and has contrasting colors and structures. The retina (located at the back of the eye) is also relatively easy to locate and focus on, because the retina is also mainly flat (when viewed through a microscope), with distinct colors and structures. The structures at the back of the eye (behind the iris) require the doctor to perform such observations through the pupil (aperture in the iris). This is possible with the correct microscope settings and adequate lighting.

[0005] Other structures such as the cornea, lens, and vitreous humor or structures within the vitreous humor cannot be easily distinguished because they are transparent or difficult to locate and visualize within the vitreous humor.

[0006] The object of the present invention is to further develop the known devices or apparatuses and methods for eye examination and / or eye treatment, in particular to improve the detection of objects in the vitreous humor.

[0007] The object of the present invention is achieved by a device for determining the position of an object of interest in an eye of a patient, in particular in the vitreous body of the eye, the device comprising means for generating at least one beam path onto the object of interest and a reference plane relative to the object of interest, wherein the device is configured to determine an object distance between the reference plane and the object of interest at the reference plane.

[0008] Since the object distance can be determined at a reference plane whose position is known, the position of the object of interest within the eye can also be precisely determined.

[0009] It should be understood that the device can generate the reference plane in various ways so that its position is precisely known. For example, the reference plane is conveniently specified by a device for making the reference plane so that the position of the reference plane is precisely known at the device.

[0010] The reference plane can be established particularly easily if known reference structures of the patient's eye can be used to establish the reference plane.

[0011] In this regard, the object of the present invention is achieved by a device for determining the position of an object of interest in an eye of a patient, in particular in the vitreous body of the eye, relative to a known reference structure, in particular a known reference structure of the eye, the device comprising means for generating at least one beam path onto the object of interest, the device being arranged to determine an object distance between the reference structure and the object of interest at a reference plane established with the aid of the reference structure.

[0012] Since the actual object distance between the object of interest and a known reference structure, preferably a known reference structure of the human body, particularly preferably a known reference structure of the human eye, can be determined at the reference plane, the position of the object of interest can be determined particularly easily and reliably.

[0013] It is useful to use known structures of the eye as reference structures, which can be easily identified during an eye examination, so that the device can be designed to be very compact and can be easily operated by the doctor.

[0014] Cumulatively or alternatively, however, it is also possible to define a reference plane by suitable technical means independently of the known eye structure, at which reference plane the object distance relative to this reference plane can be determined.

[0015] The means for establishing the reference plane may also be provided independently of the device, for example by means of an ophthalmic treatment device.

[0016] However, if the device comprises means for establishing a reference plane, the device may operate more autonomously.

[0017] In the sense of the invention, the term “at the reference plane” means in particular that the object distance between the reference plane and the object of interest is determined along the reference plane. This can be done in the reference plane or beside the reference plane.

[0018] Of particular relevance to the device are structures within the vitreous, such as vitreous opacities or floaters. Until now, these structures have been difficult to locate and visualize. They are usually small, three-dimensional, translucent, and "float" in the vitreous. Microscopes have a short depth of field due to their high magnification, resulting in poor depth perception. As a result, it is difficult to find non-planar structures. Even if they are found, it is difficult to tell where the structure is located relative to other structures of the eye, such as the lens or retina. This is especially important for positions along the optical axis. More specifically, once an object "floating" in the vitreous is in focus and can be visualized, it is difficult for the doctor to determine how close the object is to the retina or the back of the lens. The short depth of field of the microscope means that the retina will be blurred (out of focus) or not distinguishable at all. The same is true for the lens, except that its transparent nature makes it even more difficult to see.

[0019] By means of the invention, object distances in this respect, in particular object distances between the focal plane of the microscope and the object of interest in the eye, can be easily measured.

[0020] This measurement can then be reported to a physician or used for other purposes, such as reporting or machine automation purposes.

[0021] It is thus realized that the problem of determining the position of the object of interest within the eye as explained above can be solved by determining, at a defined reference plane whose position is known, the object distance from this reference plane to the object of interest by means of corresponding images.

[0022] It goes without saying that the object distance between the object of interest and the reference structure or its reference plane can be determined at this reference plane in a variety of ways, for example by means of a value table or the like, to name just one of many examples.

[0023] It is particularly advantageous to use geometrical ray optics to describe the object distances.

[0024] With regard to a particularly precise and therefore preferred configuration, it is advantageous, for example, if the device is arranged such that the object distance can be determined via the triangular geometry of a right triangle arranged between the object of interest and the reference structure.

[0025] Here, the distance segments generated at the reference plane can be set very precisely relative to the current object position.

[0026] Thus, for example, the course of a distance segment can be oriented with respect to a reference plane in the sense of the invention, which reference plane can also be formed only hypothetically.

[0027] It is particularly advantageous if the reference plane and the measuring axis or optical axis of the device enclose a right angle with one another.

[0028] For example, if a right triangle is created between the reference structure or in particular the reference plane and the object of interest, the object distance can be determined with the aid of an angle function such as the “Pythagorean theorem” or using other trigonometric functions.

[0029] It should be understood that different ratio relationships may exist between the object distance, the distance segment along the reference plane, and the at least one optical path.

[0030] For example, the bevel may be easily and more operatively generated by at least one beam path directed from a generator source of the generating device to the object of interest and passing through the reference structure or a reference plane defined therein at an angle α≠90°.

[0031] Even with an angle as low as α=1° to 5° between at least one beam path and the reference plane, the object distance can be determined very well by means of the beam geometry.

[0032] Preferably, however, a larger angle α=10° to 60° is arranged between at least one beam path and the reference plane in order to be able to determine the corresponding object distance more precisely.

[0033] Here, the first right angle side is preferably identical to the object distance, wherein an imaginary line of the object distance is arranged orthogonally to the reference plane.

[0034] Preferably, the second right-angled leg is arranged such that it extends along the reference plane. Advantageously, the second right-angled leg may be arranged as a distance segment in the reference plane, or alternatively, extends as a distance segment parallel to the distance segment in the reference plane.

[0035] In this regard, it is advantageous that the device is arranged such that: at least one first of the right-angled sides of the right-angled triangle is determined by the object distance, at least one second of the right-angled sides of the right-angled triangle is determined at a reference plane, and the hypotenuse of the right-angled triangle is determined by at least one beam path.

[0036] As already mentioned, the object distance can be determined by means of the beam geometry in a number of structurally simple and programmatically simple ways.

[0037] For example, a distance segment of a distance segment provided in the sense of the present invention may be defined by two markings generated relative to a reference plane.

[0038] Suitable markings can in turn be generated by one or more beam paths at the reference plane, advantageously directly by the device for generating at least one beam path.

[0039] In this way, the device comprises, in addition to the means for generating at least one beam path, also means for generating a marking at the reference plane or at the distance segment.

[0040] For detecting the markings, it is advantageous if the device has an imaging system for detecting the markings at the reference plane.

[0041] A suitable optical imaging system can be designed in a particularly simple manner if the imaging system has a camera.

[0042] It will be appreciated that the imaging system of any other ophthalmic treatment device may also be used, which has the advantage that the device can be particularly simple in design.

[0043] The optical imaging system expediently has two, three or more beam paths, whereby a plurality of markings can ideally be generated simultaneously, so that the distance bins can be determined with a small or negligible time delay.

[0044] For this purpose, the optical imaging system can advantageously have two or more optical imaging devices.

[0045] The beam path may be provided by an optical imaging system such as a camera or the like.

[0046] It should be understood that the means for generating at least one light beam path (referred to as "generating means") may be implemented in different ways.

[0047] For example, the generating means may comprise a laser source, the laser beam of which is directed towards the object of interest and thus passes through the reference plane.

[0048] A beam path in the sense of the invention can also be generated and provided by means of a light source, such as a laser source or the like.

[0049] Accordingly, it is advantageous if the device has suitable technical equipment, by means of which a corresponding beam path can be generated and provided.

[0050] The object distance can therefore be advantageously determined in the sense of the invention if the device is arranged such that the object distance can be determined from two markings generated at the reference plane by at least one beam path passing through the reference plane and arranged at a distance interval from one another.

[0051] If the markings of two or more optically generated light beams are generated or arranged simultaneously at the reference plane, the distance segments can be determined almost without time delay. This also allows the object distance to be determined in the shortest possible time.

[0052] However, in this design variation, two beam path sources spaced apart along the reference plane are required.

[0053] Here, the apparatus may have two or more generating means, or alternatively, the apparatus is configured such that a single generating means also has two or more such beam path sources.

[0054] If applicable, the device also has a deflection device in which the beam path of a single beam path source is divided into at least two partial optical beam paths, whereby a plurality of beam paths can be provided simultaneously in a particularly simple manner.

[0055] For example, two spaced apart markers of a single optical path may be used, particularly when the reference plane moves relative to the object of interest.

[0056] Cumulatively or alternatively, beam paths generated in a time-delayed manner and from different angles may be used.

[0057] Advantageously, therefore, markings of spaced-apart distance bins can be generated in a time-shifted manner.

[0058] The advantage of the latter configuration is that a single beam path source is sufficient to determine the object distance in the sense of the present invention.

[0059] A further advantageous design variant provides that the device is designed such that the object distance can be determined by image displacement relative to markings which are generated by at least one beam path passing through the reference plane and which are spaced apart from one another by distance segments.

[0060] Such markings generated by image shifting may have different shapes relative to the reference plane.

[0061] For example, suitable markers may represent image information of an object of interest imaged at a reference plane, whereby distance segments between markers then represent a displacement distance between two image information imaged from different angles and / or two image information imaged at different times.

[0062] The marking may also include image information or at least a portion thereof.

[0063] In any case, the device can advantageously implement geometrical beam optics if the device is arranged such that at least one beam path is arranged at an angle α different from 90° relative to the reference plane, while the object distance is oriented at right angles relative to the reference plane. In this case, the distance segment between the two markings extends along the reference plane.

[0064] It is particularly advantageous if the device comprises an optical imaging system for imaging a reference plane, and the optical imaging system has one or more beam paths for imaging an image of the object of interest at the reference plane, wherein the device is configured to determine the object distance by an image shift amount of the image imaged at the reference plane along the reference plane or by a distance segment of two optical marks generated at the reference plane. In this way, the device can be constructed to easily determine the object distance.

[0065] The object distance can be determined particularly accurately if it is proportional to the amount of image shift at the reference plane.

[0066] Particularly in this case, it is advantageous if the image of the object of interest imaged at the reference plane can be shifted to a further image when the reference plane is shifted relative to the object of interest in order to determine the object distance.

[0067] Here, the reference plane is displaced relative to the object of interest along an imaginary line along the distance of the object.

[0068] It is useful that the distance segment between two markings and the object distance are related to each other so that the object distance can be determined from the distance segment. The invention is also characterized by the fact that by means of at least one beam path suitable markings can be generated at the reference plane which provide distance segments proportional to the desired object distance.

[0069] If the device is arranged such that the focal plane can be arranged at the object of interest, the object distance can be determined with a particular operational reliability.

[0070] In order to advantageously support the determination of the object distance, the reference plane is preferably a plane which is displaceable parallel to the focal plane, so that the object distance is arranged to extend orthogonally to both planes.

[0071] Advantageously, the device is arranged such that the beam paths in the focal plane can be focused to a common focus.

[0072] Alternatively, the beam paths in the focal plane may be focused at different focal points.

[0073] If the device is arranged such that at least one beam path is directed through the reference plane onto the object of interest, the marking can be generated more accurately at the reference plane.

[0074] Furthermore, it is advantageous if the device is arranged such that at least one beam path is arranged at an angle α to the object distance, wherein the object distance is arranged orthogonally to the reference plane. This also helps to more accurately determine the object distance based on the markings generated relative to the reference plane or the distance segments of the path relative to the reference plane.

[0075] The construction of the device can be further improved or simplified if the device is arranged such that the object distance includes an optical axis of the device.For a very simple construction, the optical axis can be the machine direction of the device, wherein the machine direction is the working direction of the device.

[0076] Furthermore, the device can be further advantageously developed if the optical axis of the device comprises the optical axis of an eye observation and / or treatment device, such as the optical axis of an ophthalmic microscope or the like.

[0077] If the beam paths at least partially enclose an observation angle with one another, the object distance, in particular the object distance relative to a reference plane, can advantageously be determined. For example, two beam paths passing through a reference plane enclose such an observation angle with one another.

[0078] In order to be able to image the optical marking in an easily determinable manner at the reference plane, it is advantageous if the reference plane is arranged in front of or behind the focal plane relative to the optical imaging system.

[0079] An advantageous embodiment provides that the device has an ophthalmic microscope, the focal length of which is in particular identical to the focal length of the optical imaging system. This allows the object distance to be determined in a structurally simple and precise manner.

[0080] In this case, the object of the invention is also achieved by an ophthalmic instrument for treating a patient's eye with an ophthalmic microscope, which is characterized by a device having at least one of the features described herein. The ophthalmic instrument is further advantageously developed by the device according to the invention, so that an eye examination or eye treatment can be performed more accurately and more quickly.

[0081] The object of the present invention is further achieved by a method for operating an apparatus for determining the position of an object of interest in an eye of a patient, in particular in the vitreous body of the eye, wherein at least two beam paths cross each other at a common intersection point through a reference plane, wherein at least two beam paths each image the intersection point or its vicinity as spaced-apart images at the reference plane, and wherein the intersection point F and the reference plane are shifted relative to each other, whereby the images are shifted at the reference plane, and the original distance from the intersection point to the reference plane is determined by the amount of the shift of these images.

[0082] Advantageously, the position of the intersection point relative to the reference plane and the position of the plane passing through the intersection point relative to the reference plane can be determined by measuring a corresponding distance segment at the reference plane and associating the distance segment with the object distance to be determined.

[0083] Therefore, the distance of an object extending in the machine direction of the device is not measured along its actual longitudinal extension, but rather by a distance segment extending transversely to the object distance. The distance segment is measured along its longitudinal cross-sectional extension, which is arranged transversely to the machine direction or the object distance.

[0084] This means that the desired object distance can be determined particularly accurately by means of the distance segment at a precisely defined reference plane.

[0085] This also applies in particular to the device for carrying out the method.

[0086] Advantageously, the at least two beam paths form an observation angle with respect to each other such that the at least two beams can intersect each other and further generate spaced-apart markings at the reference plane.

[0087] The value of this observation angle is between 0° and 180° so that the beam paths can pass through the reference plane when they subsequently cross at the intersection point.

[0088] Preferably, the observation angle has a value between 10° and 90°, which enables a reliable determination of the object distance at the reference plane.

[0089] In order to be able to construct the device with the reference plane more compactly, it is advantageous if the value of the observation angle is between 30° and 50°, or preferably between 35° and 45°. Even with these values, the object distance can be determined exactly at the reference plane. Furthermore, the beam path can be arranged to pass well through the pupil of the eye.

[0090] It is also useful to select the viewing angle depending on the position of the intersection point relative to the reference plane.

[0091] The object of the present invention is further achieved by a method for operating a device for determining the position of an object of interest in an eye of a patient, in particular in the vitreous body of the eye, wherein a reference plane is generated which is orthogonal to a measuring axis of the device, wherein at least one optical path passing through the reference plane intersects the measuring axis at a common intersection point, and wherein at least one optical path generates a mark at the crossing point at the reference plane in order to determine the distance between the intersection point and the reference plane at the reference plane.

[0092] The markings can be designed in different ways, as already explained above.

[0093] In order to obtain a distance segment that can be measured well at the reference plane, it is advantageous to generate additional markings at the reference plane.

[0094] Preferably, additional markings are also generated by the beam path passing through the reference plane.

[0095] One method variant provides that the beam paths are generated sequentially in a time-shifted manner. This allows the method itself to be operated with only a single device for generating at least one beam path, which also allows the corresponding device to be constructed with fewer components.

[0096] If the beam paths generated in a time-shifted manner are also generated in a position-shifted manner and form an imaginary observation angle with respect to one another, the distance segment between two spaced-apart markings at the reference plane can be easily generated.

[0097] If a focal plane is defined at the intersection point of two intersecting beam paths, the distance of objects lying between the two planes can be determined very reliably.

[0098] Cumulatively or alternatively, one or more focal planes may also be defined at a position different from the intersection point defined by the intersecting beam paths, if advantageous.

[0099] If the object distance is orthogonal to the two planes, the reference plane and the focus plane are arranged as planes parallel to each other.

[0100] If the reference plane is defined by at least one camera, the reference plane can be realized in a very simple manner at the device, both from a process technology and a design perspective.

[0101] The object of the invention is also achieved by a method for determining the position of an object of interest in an eye of a patient, in particular in the vitreous body of the eye, wherein an object distance between the object of interest and known reference structures of the eye is determined at a reference plane defined by the reference structures.

[0102] By means of the known reference structure of the eye, the position of the reference plane is known and the object distance to the object of interest can be determined exactly at the reference plane.

[0103] Advantageously, the distance, in particular the object distance, is determined by the ratio of the sides of a right triangle.

[0104] The object of the present invention is also achieved by a specific method for determining the position of an object of interest in an eye of a patient, in particular in the vitreous body of the eye, wherein the object of interest is arranged in or near a generated focal plane, wherein known anatomical eye structures of the eye are arranged in a generated reference plane, wherein at least two optical paths through the reference plane are focused at or near the focal plane, wherein one or more image shifts of at least one image focused relative to the focal plane are determined at the reference plane when the focal plane and the reference plane are moved relative to each other, and wherein the distance between the focal plane and the reference plane is determined with the aid of the image shifts at the reference plane.

[0105] It has been shown that the position or location of an object of interest in the eye can be determined simply and precisely using this method. For this purpose, a distance segment is determined at a reference plane, which is obtained by measuring the image displacement, as described above. The image at the reference plane is used as a marker.

[0106] In the sense of the present invention, the term "nearby" refers to a distance of less than 10 mm, preferably less than 5 mm from the actual focal plane.

[0107] The object of the present invention is also achieved by another specific method for determining the position of an object of interest in an eye of a patient, in particular in the vitreous body of the eye, wherein the object of interest is arranged in or near a generated focal plane, wherein known anatomical eye structures of the eye are arranged in a generated reference plane, wherein at least one light beam path is focused at or near the focal plane through the reference plane, and wherein a distance segment between two marks generated by at least one light beam path at the reference plane is determined, and wherein the distance between the focal plane and the reference plane is determined at the reference plane by the determined distance segment.

[0108] Moreover, with this method, the position of the object of interest in the eye can be accurately measured.

[0109] The distance between two planes or the object distance determined in this way can also be referred to as plane distance.

[0110] Based on the now accurately determined object distance, the practitioner or doctor can perform eye treatment.

[0111] An advantageous method variant provides that the determined object distance is made available to the automatically operated treatment machine. This allows the operation of the appropriate treatment machine to be made more precise.

[0112] It should also be noted that, in the context of this patent application, indefinite articles and indefinite quantity indicators such as "one...", "two...", etc. should generally be understood to indicate at least, that is, "at least one...", "at least two...", etc., unless the context or the specific text of a particular paragraph clearly indicates that it only refers to "exactly one...", "exactly two...", etc.

[0113] At this point, it should also be mentioned that in the context of this patent application, the term "particularly" should always be understood as introducing optional, preferred features through this expression. The term should not be understood as "in fact" or "i.e.".

[0114] In this case, it is also claimed that the described method can be supplemented by further technical features described here, in particular by features of the device, in order to advantageously further develop the method or to be able to more precisely represent or formulate the method specifications.

[0115] It is to be understood that, if necessary, the features of the solutions described above or in the claims may also be combined in order to be able to implement the advantages and effects achievable herein in a corresponding cumulative manner.

[0116] Furthermore, further features, effects and advantages of the present invention are explained with reference to the accompanying drawings and the following description, in which an exemplary first device for determining a position of an object of interest is shown and described.

[0117] Components which correspond essentially to each other in the individual figures, at least with regard to their function, may be identified here with the same reference numerals, so that these components do not have to be numbered and explained in all figures.

[0118] The following figures show:

[0119] Figure 1 schematically shows a model view of a first device for determining a position of an object of interest, the first device having a dual imaging system;

[0120] Figure 2 Schematically shows Figure 1 another view of the first device;

[0121] Figure 3 schematically shows another model view of an alternative device for determining the position of an object of interest, the alternative device having an integrated ophthalmic microscope;

[0122] Figure 4 Schematically shows Figure 3 A detailed view of an alternative device is shown, wherein the reference plane passes through a known iris reference structure;

[0123] Figure 5 schematically shows another model view of another device for determining a position of an object of interest, the other device having an arrangement including a dual camera;

[0124] Figure 6 schematically shows another model view of another device for determining a position of an object of interest, the other device having a device including a depth camera for time-of-flight measurement;

[0125] Figure 7 schematically shows another model view of another apparatus for determining the position of an object of interest, the other apparatus having means including slit lamp translation tracking;

[0126] Figure 8 schematically shows another model view of another device for determining a position of an object of interest, the other device having means including at least one camera for depth perception;

[0127] Fig. 9 schematically shows another model view of another device for determining the position of an object of interest, the other device comprising means for printing a pattern on a contact lens and means comprising a camera for focusing said pattern; and

[0128] Fig.10 A further model view of a further device for determining a position of an object of interest is schematically shown, the further device having a device comprising OCT detection or ultrasound A-type scanning of the object of interest.

[0129] Figure 1 and Figure 2 The device 1 shown in FIG. 1 is a first embodiment example I of the invention for determining a position 2 of an object of interest 3 in an eye 4 of a patient (not shown in detail here).

[0130] The object of interest 3 is a foreign structure such as a so-called floater or the like within the eye 4 , more precisely within the vitreous body 5 of the eye 4 .

[0131] The device 1 has a machine axis 6 in a machine direction 7 , in the longitudinal extension of which an optical axis 8 of the device 1 can be defined.

[0132] Furthermore, the device 1 has a device 10 for generating two beam paths 11 and 12 .

[0133] In this case, the generating device 10 comprises two imaging systems 13 and 14 having two camera units 15 and 16 .

[0134] The optical axis 8 of the device 1 is defined here by the viewing direction 17 of the imaging systems 13, 14. The viewing direction 17 is in the machine direction 7.

[0135] Furthermore, the device 1 has means 20 for establishing a reference plane Y, which may be implemented by the imaging systems 13 , 14 or the camera units 15 , 16 .

[0136] In this first embodiment, the reference plane Y is placed as a cross-sectional plane (not separately numbered) through a known eye structure 22 , which here is the iris of the eye 4 (not separately numbered) and thus represents a known reference structure 23 .

[0137] The two optical paths 11 and 12 enclose an observation angle θ with each other, so that the two optical paths 11 and 12 coming from different directions intersect at a common intersection point F.

[0138] The distance between the imaging systems 13 , 14 and the intersection point F defines the focal length f of the device 1 .

[0139] In this first embodiment, the point of intersection F defines a focus F of the focal plane E. As shown in FIG.

[0140] In this first embodiment, the intersection point F is selected such that the object of interest 3 is also located at the intersection point.

[0141] Furthermore, the two beam paths 11 , 12 and the reference plane Y are arranged relative to one another in such a way that the two beam paths 11 and 12 pass through the reference plane Y.

[0142] In order to determine the position 2 of the object of interest 3 within the eye 4 , the object distance C between the intersection point F and the reference structure 23 or between the focal plane E and the reference plane Y is now determined.

[0143] In particular, Figure 1 A simplified schematic diagram of the apparatus 1 and a cross section of the eye 4 is shown. The two imaging systems 13, 14 of the apparatus 1 are arranged to focus at the same position (intersection point F), but separated by an observation angle θ.

[0144] In this embodiment example, the two imaging systems 13 , 14 are identical and comprise appropriate optical components to image the focal plane E at the intersection point F.

[0145] A camera unit 15 or 16 has been added to each imaging system 13, 14 to capture the resulting image. An object located near the focal plane E will be imaged by the two imaging systems 13, 14 to produce two similar images O1 and O2 (see also Figure 2 ), images O1 and O2 will share the same content and have similar size and spatial arrangement.

[0146] However, for an object located behind or in front of the focal plane E, such as an iris located at an object distance C in front of the focal point F (object of interest 3), the images O1 and O2 will be different.

[0147] The two images O1 and O2 will still share the same content, have similar size and spatial arrangement, but the content will be shifted by an amount proportional to the object distance C, e.g. Figure 2 is shown in more detail in .

[0148] Figure 2Another schematic diagram of the device 1 is shown, wherein the imaging systems 13, 14 and the camera units 15, 16 are removed for simplicity and is a 3D view.

[0149] The two squares A1 and A2 represent the image planes 25 of the two imaging systems 13 and 14 at the reference plane Y.

[0150] Imaging systems 13 and 14 produce images of an object (large solid vertical arrow labeled O) located at their common focus F. The two images of O are labeled O1 and O2.

[0151] When the object of interest 3 moves an object distance C towards the two imaging systems 13 and 14 , as indicated by the large dashed arrows labeled O′, the images O1 and O2 generated by O′ are shifted on the image plane 25 to form new images at O′1 and O′2 .

[0152] The image shifts are labeled y1 and y2.

[0153] Since the observation angle θ is fixed, the displacement amounts y1 and y2 can be directly related to the object distance C.

[0154] The images O1 and O2 and the shifted images O'1 and O'2 may be considered as marks 27, 28 at the reference plane Y or include appropriate marks 27, 28 at the reference plane Y, wherein the marks 27 and 28 are spaced apart from each other by a distance B (not shown here, see Figure 4 ).

[0155] Therefore, the object distance C can be determined easily and very accurately at the reference plane Y.

[0156] Preferably, the front of the iris is aligned with the ophthalmic microscope 150 (see Figure 3 ) is determined, but other reference structures 23 of the patient's eye 4 can also be used.

[0157] in this case, Figure 3 Another embodiment example II. of an alternative device 100 for determining a position 102 of an object of interest 103 within an eye 104 of a patient, in particular within a vitreous body 105 of the eye 104, is shown. The alternative device is similar to Figure 1 and Figure 2 The device 1 shown, however, has in addition an ophthalmic microscope 150. More specifically, the alternative device 100 in this further embodiment example has been integrated into an ophthalmic microscope 150.

[0158] Ophthalmic Microscope 150 Figure 3 Only its objective lens 151 is shown.

[0159] The alternative device 100 also has a machine direction 107 , in the longitudinal extension of which a machine axis 106 or an optical axis 108 of the alternative device 100 may be defined.

[0160] Figure 3 Another schematic diagram of an alternative device 100 and a cross section of a patient's eye 104 is shown, wherein the iris is used as a reference structure 123 or known eye structure 122 . Figure 3 The orientation is that the patient (not shown, only the patient's eye 104 is shown) is in Figure 3 at the top of the .

[0161] In this configuration, the two imaging systems 113 and 114 share a microscope objective 151 and are configured such that their focal planes (not separately numbered) coincide with the focal plane of the ophthalmic microscope 150 (ie, are in one common focal plane E).

[0162] In this further embodiment example, the imaging systems 113 and 114 are positioned parallel to each other, wherein the binocular observation path 153 has two parallel beam paths 111 and 112 of the ophthalmic microscope 150 , which are separated by a beam path distance D.

[0163] The beam paths 111, 112 (generated by the device 110 for generating beam paths) are arranged parallel to the optical axis 108 of the device 100 up to the objective 151, and in this embodiment, the optical axis 108 of the device 100 is formed by the ophthalmic microscope 150. The refractive power of the objective 151 creates an observation angle θ between the two beam paths 111 and 112 after the objective 151.

[0164] The exact configuration of the alternative device 100 or imaging systems 113, 114 and camera units 115, 116 may vary, and they may be configured to sample light along the binocular observation path 153 using other beam splitters (not shown), or they may be located outside the observation path 153 and their respective beam paths 111, 112 may be folded by mirrors (not shown) or other optical components (not shown) to enable them to fit within the ophthalmic microscope 150.

[0165] The key point is that they all image the same object near the focal plane E from different angles.

[0166] In any case, the camera units 115, 116 will generate two images O1 and O2 (see Figure 2 These digital images O1 and O2 are then processed by a processor running software algorithms and codes.

[0167] The images O1 and O2 are compared and the difference in the position of the same object in each image O1 and O2 is found. It is this difference that is used to determine the object distance C of the object from the reference plane Y.

[0168] The apparatus 1 and 100 described above use two camera units 15 , 16 or 115 , 116 , however, it is conceivable that the apparatus 1 or 100 uses only one camera unit 15 or 16 or 115 or 116 to collect the images O1 and O2 .

[0169] The key is that the two images O1 and O2 are images of the same object but imaged from different angles, and at least one of the images O1 and O2 needs to be at a different angle to the machine axis 6 or the microscope optical axis 8 or 108, especially the ophthalmic microscope 150 can be moved along the axis 6, 8 or 108.

[0170] In general, the imaging system 13 , 14 or 113 , 114 and the ophthalmic microscope 150 do not necessarily share the same focal plane E.

[0171] The imaging systems 13 , 14 or 113 , 114 may have different focal planes E located at positions more suitable for imaging structures of interest of the eye 4 or 104 , such as the iris.

[0172] The relative distance C between planes E, Y can be processed in software.

[0173] Furthermore, a triangular geometry 155 of a right triangle 156 is arranged between the object of interest 103 and the reference structure 123 , by means of which the object distance C can be determined by means of an angular function. In this case, the optical path 111 is positioned behind the objective 151 at an angle α relative to the machine axis 106 or optical axis 108 .

[0174] The device 100 is integrated together with an ophthalmic microscope 150 in an ophthalmic instrument 150A.

[0175] Further alternative concepts are explained based on the following description.

[0176] Figure 4 Shows Figure 3 The same apparatus 100 is shown with an ophthalmic microscope 150, but without the eye 104, the intersection plane or reference plane Y is placed at the location of the iris, which is a known eye structure 122 (see Figure 3 ).

[0177] In addition, two beam paths 111 and 112 are projected onto the focal plane E from within the ophthalmic microscope 150 .

[0178] The two beam paths 111 and 112 represent two narrow beams, which are located at the objective lens 151 at a beam path distance D and are located to intersect at the focal plane E.

[0179] The two beam paths 111 and 112 of light will project two light spots 157 and 158 at the reference plane Y, which are separated by a distance segment B.

[0180] These light spots 157 and 158 can be regarded as markings 127 , 128 , wherein the markings 127 and 128 are spaced apart from each other at the reference plane Y by a distance section B.

[0181] Through geometry, the mathematical relationship between B and C is as follows:

[0182] B=D / F×C=>C=F / D×B

[0183] In this case, the required object distance C can also be easily determined by the alternative device 100 .

[0184] In particular, the imaging systems 113, 114 (including camera units 115, 116, optical components (such as objective lens 151, etc.) and a computer) can measure the distance segment B between the two light spots 157 and 158 or marks 127, 128 on the reference plane Y, thereby determining the object distance C.

[0185] Some further remarks on the design and implementation of the apparatus 1 , 100 of the present invention.

[0186] The arrangement of the embodiment examples described above utilizes two rays or their two beam paths 111, 112 and their relative spacing at the reference plane Y (spots 157, 158 or markings 127, 128) to determine the object distance C of the reference plane Y in front of the focal plane E. Several alternative configurations to this may be used.

[0187] Alternative 1:

[0188] More than two light rays or beam paths 111 , 112 may be used.

[0189] For example, three or more beam paths 111, 112 may be used to form more than two light spots 157, 158 or more than two marks 127, 128 at the reference plane Y. This arrangement may require more measurements and averages. An advantage of this arrangement may be that, for example, it may offset any small angles or curvatures of the reference plane Y or the intersecting planes.

[0190] Alternative 2:

[0191] Instead of two rays or two beam paths 111, 112, a single beam of size A (diameter of circular cross section) can be used which can be focused to a small spot at focal plane E. In this arrangement, the measured value B will not be the separation but the beam size A (diameter of circular cross section) on reference plane Y or the intersection plane.

[0192] Alternative 3:

[0193] Instead of a beam with a circular cross section (beam paths 11, 12; 111, 112), a beam with a different shape may be used. For example, a beam with a triangular or arrow-shaped cross section. It is further noted that a beam with an asymmetric cross section shape 1 (e.g., a triangle) may be advantageous because the projected image on the reference plane Y will be inverted if the reference plane Y is behind or in front of the focal plane E.

[0194] Alternative 4:

[0195] Instead of a beam with a circular cross section (beam paths 11, 12; 111, 112), a patterned shape (such as parallel lines, concentric circles or other suitable pattern) can be projected onto the reference plane Y. The patterns can be slightly angled to each other to produce visual fringes (moire interference patterns) when they overlap. The fringes can be used to make very accurate distance measurements.

[0196] Alternative 5:

[0197] Instead of the two beams 11, 12; 111, 112 converging to a single point at the focal plane E (such as an intersection point or focus F), the two beams can be configured to have separate points at the focal plane E. This can be achieved by directing the two beams in a different way within the ophthalmic microscope 150. This configuration may be advantageous if there is an optimal separation distance segment B for the imaging system 13, 14; 113, 114 to measure B. If so, the device 1, 100 can be configured to ensure that the distance segment B falls within an optimal range of appropriate values ​​of the object distance C.

[0198] Alternative 6:

[0199] The light beams (beam paths 11, 12; 111, 112) can be focused to a plane different from the microscope focal plane E. For example, this plane can be located at the average position of the reference plane Y (when observing the vitreous body). This can have the advantage that the images (O1 and O2 and O'1 and O'2) produced by the light beams (beam paths 11, 12; 111, 112) at the reference plane Y will be in sharp focus, which will potentially improve the ability of the imaging system 13, 14; 113, 114 to measure the distance segment B.

[0200] Refer to the following Figures 5 to 10 Schematically show further alternative embodiment examples of how the devices 1, 100 explained here can be designed or supplemented alternatively in terms of construction, although the corresponding alternative concepts of these devices are not shown in further detail:

[0201] Figure 5 A first other alternative embodiment example III is shown and is based on a horizontal stereo vision method. The basic idea is that dual cameras take pictures of the same scene at two different locations and restore the depth at each pixel. One advantage here is that a safe treatment area can be determined by measuring the parallax of the images taken by the cameras. The system can achieve good resolution and repeatability by measuring laser depth perception.

[0202] Figure 6 A second other alternative embodiment example IV. is shown and is based on the use of a depth camera using time-of-flight measurement. The object distance C is determined based on the measured flight time of the light beam between a device for generating at least one suitable beam path and a detector unit (such as a camera unit, etc.) spaced therefrom, wherein the object distance C = 1 / 2 × c × t, wherein c = speed of light, t = time of flight. A suitable computer program is used to take into account the time delay caused by the reflection of the light pulse from the laser or LED from a reflective curved surface (such as the cornea).

[0203] Figure 7 A third other alternative embodiment example V. is shown and is based on slit lamp translation tracking, which can track the movement of the laser transmission head in each direction by electromechanical sensor sensing. The sensor signal is captured by the CPU and processed by software to track the position. One advantage is that this configuration is easy to implement. This can be cost-effective if no stepper motor modules are involved.

[0204] Figure 8 A fourth other alternative embodiment example VI. is shown and is based on depth perception in a single camera. No focus adjustment is required. If the retinal image is in focus, a warning is displayed or a measurement reference is set. Another camera or the same camera can be used to detect proximity to the iris and a warning is issued if the iris is almost in focus. Here, in particular, by identifying the iris / lens and retina as reference points, a safe treatment area can be determined.

[0205] Another approach could be to use out-of-focus blur analysis to estimate depth perception, where the software detects image blur and simultaneously commands the liquid lens to correct the image. The current applied to the liquid lens for image correction is read by the software to quantify the amount of depth change that the target "eye" is displaced by. An advantage here is that out-of-focus blur analysis can provide a strong correlation with detecting depth perception.

[0206] Fig. 9 A fifth other alternative embodiment example VII. is shown and is based on printing a pattern on or around a contact lens and focusing the camera on it. The advantage here is that the cornea has a marking reference, and the camera can detect this strong reference to perceive depth.

[0207] Fig.10 A sixth other alternative embodiment example VIII. is shown and is based on the use of OCT (Optical Coherence Tomography) to detect floater locations or using Ultrasound A-Scans. An advantage here is that OCT can provide accuracy and reliability for this purpose.

[0208] All of the above-mentioned alternative embodiments or concepts solve the present problem of the present invention even without the other features of the present invention.

[0209] However, the described alternative embodiment examples or concepts may also be combined with other features in order to further develop a device that is consistent with the spirit of the invention.

[0210] At this point it should be explicitly pointed out that, if necessary, the features of the solutions described above or in the claims and / or drawings may also be combined in order to be able to implement or achieve the explained features, effects and advantages in a corresponding cumulative manner.

[0211] It should be understood that the embodiment examples explained above are only first embodiments of the device according to the present invention. In this respect, the embodiments of the present invention are not limited to these embodiments.

[0212] All features disclosed in the application documents are considered to be essential to the invention insofar as they are novel over the prior art, either individually or in combination.

[0213] List of reference numerals:

[0214] 1 Equipment

[0215] 2 Position or location

[0216] 3 Objects of interest

[0217] 4 Eyes

[0218] 5. Vitreous

[0219] 6 Machine axis or measuring axis

[0220] 7 Machine direction

[0221] 8 Optical axis

[0222] 10. means for generating at least one beam path

[0223] 11 First beam path

[0224] 12 Second beam path

[0225] 13. First Imaging System

[0226] 14 Second Imaging System

[0227] 15 First Camera Unit

[0228] 16 Second Camera Unit

[0229] 17 Observation direction

[0230] 20 Device for establishing a reference plane

[0231] 22 Known structures of the eye

[0232] 23 Known reference structures

[0233] 25 Image plane

[0234] 27 First Mark

[0235] 28 Another mark separated by

[0236] 100 Alternative equipment

[0237] 102 Position or location

[0238] 103 Objects of interest

[0239] 104 Eyes

[0240] 105 Vitreous

[0241] 106 Machine axis or measuring axis

[0242] 107 Machine direction

[0243] 108 Optical axis

[0244] 110 means for generating at least one beam path

[0245] 111 First beam path

[0246] 112 Second beam path

[0247] 113 First Imaging System

[0248] 114 Second Imaging System

[0249] 115 First Camera Unit

[0250] 116 Second Camera Unit

[0251] 117 Observation direction

[0252] 122 Known structures of the eye

[0253] 123 Known reference structures

[0254] 127 First Mark

[0255] 128 Another mark separated by

[0256] 150 Ophthalmic Microscope

[0257] 150A Ophthalmic Instruments

[0258] 151 Objective

[0259] 153 Binocular Observation Path

[0260] 155 Triangle geometry

[0261] 156 - Right Triangle

[0262] 157 First Light Spot

[0263] 158 Another Light Spot

[0264] f Focal length

[0265] B Distance Segment

[0266] C Object distance

[0267] D Beam path distance

[0268] E Focal plane

[0269] F Intersection Point

[0270] Y reference plane or intersection plane

[0271] θ Observation angle

[0272] α Angle

[0273] I. Example of Embodiment

[0274] II. Second Embodiment Example

[0275] III. First Alternative Embodiment Example

[0276] IV. Second Alternative Embodiment Example

[0277] V. Third Alternative Embodiment Example

[0278] VI. Fourth Alternative Embodiment Example

[0279] VII. Fifth Alternative Embodiment Example

[0280] VIII. Sixth Alternative Embodiment Example

Claims

1. A device (1; 100) for determining a position (2; 102) of an object of interest (3; 103) in an eye (4; 104) of a patient, in particular in the vitreous body (5; 105) of the eye (4; 104), the device having a device (10; 110) for generating at least one beam path (11, 12; 111, 112) and a reference plane (Y) relative to the object of interest (3; 103), the device (1; 100) being arranged to determine an object distance (C) between the reference plane (Y) and the object of interest (3; 103) at the reference plane (Y).

2. The device (1; 100) according to claim 1, characterized in that The reference plane (Y) can be established from a known reference structure (23; 123) of the patient's eye (4; 104).

3. The device (1; 100) according to claim 1 or 2, characterized in that The device (1; 100) is arranged such that the object distance (C) can be determined by means of a triangle geometry (155) of a right triangle (156) arranged between the object of interest (3; 103) and the reference structure (23; 123).

4. The device (1; 100) according to any one of claims 1 to 3, characterized in that The device (1; 100) is arranged such that: at least a first right-angled side of a right-angled triangle (156) is defined by the object distance (C), at least a second right-angled side of the right-angled triangle (156) is defined at the reference plane (Y), and the hypotenuse of the right-angled triangle (156) is defined by the at least one beam path (11, 12; 111, 112).

5. The device (1; 100) according to any one of claims 1 to 4, characterized in that The device (1; 100) comprises at least one optical imaging system (13, 14; 113, 114) for detecting a mark (27, 28; 127, 128) formed at the reference plane (Y).

6. The device (1; 100) according to any one of claims 1 to 5, characterized in that The device (1; 100) is arranged so that the object distance (C) can be determined by two marks (27, 28; 127, 128) generated at the reference plane (Y) by the at least one beam path (11, 12; 111, 112) passing through the reference plane (Y), the marks (27, 28; 127, 128) being arranged to be separated from each other by a distance segment (B).

7. The device (1; 100) according to claim 6, characterized in that The markings (27, 28; 127, 128) spaced apart by distance segments (B) can be generated in a time-shifted manner.

8. The device (1; 100) according to any one of claims 1 to 7, characterized in that The device (1; 100) is arranged so that the object distance (C) can be determined by image shifting relative to the markings (27, 28; 127, 128), the markings being generated by the at least one beam path (11, 12; 111, 112) passing through the reference plane (Y), the markings (27, 28; 127, 128) being spaced apart from each other by a distance segment (B).

9. The device (1; 100) according to any one of claims 1 to 8, characterized by an optical imaging system (13, 14; 113, 114) for imaging the reference plane (Y) and having one or more beam paths (11, 12; 111, 112) for imaging an image (O1, O2; O'1, O'2) of the object of interest (3; 103) at the reference plane (Y), wherein The device (1; 100) is configured to determine the object distance (C) by an image shift amount (y1, y2) of an image (O1, O2; O'1, O'2) imaged at the reference plane (Y) along the reference plane (Y) or by a distance segment (B) of two optical marks (27, 28; 127, 128) generated at the reference plane (Y).

10. The device (1; 100) according to claim 9, characterized in that The object distance (C) is proportional to the image shift amount (y1, y2) at the reference plane (Y).

11. The device (1; 100) according to any one of claims 1 to 10, characterized in that When the reference plane (Y) is displaced relative to the object of interest (3; 103), the image (O) of the object of interest imaged at the reference plane (Y) can be displaced to a further image (O') in order to determine the object distance (C).

12. The device (1; 100) according to any one of claims 1 to 11, characterized in that The distance segment (B) between two markings (27, 28; 127, 128) and the object distance (C) are correlated with one another, so that the object distance (C) can be determined with the aid of the distance segment (B).

13. The device (1; 100) according to any one of claims 1 to 12, characterized in that The device (1; 100) is arranged such that a focal plane (E) can be arranged at the object of interest (3; 103).

14. The device (1; 100) according to any one of claims 1 to 13, characterized in that The beam paths (11, 12; 111, 112) are focussable to a common focus (F) in the focal plane (E).

15. The device (1; 100) according to any one of claims 1 to 13, characterized in that The beam paths (11, 12; 111, 112) are focussable at different focal points in the focal plane (E).

16. The device (1; 100) according to any one of claims 1 to 15, characterized in that The device (1; 100) is arranged such that the at least one beam path (11, 12; 111, 112) is directed through the reference plane (Y) onto the object of interest (3; 103).

17. The device (1; 100) according to any one of claims 1 to 16, characterized in that The device (1; 100) is arranged such that the at least one beam path (11, 12; 111, 112) is arranged at an angle (α) to the object distance (C), wherein the object distance (C) is arranged orthogonally to the reference plane (Y).

18. The device (1; 100) according to any one of claims 1 to 17, characterized in that The device (1; 100) is arranged such that the object distance (C) includes an optical axis (8; 108) of the device (1; 100).

19. The device (1; 100) according to any one of claims 1 to 18, characterized in that The beam paths (11, 12; 111, 112) enclose a viewing angle (θ) with one another, at least in sections.

20. The device (1; 100) according to any one of claims 1 to 19, characterized in that The reference plane (Y) is arranged in front of or behind the focal plane (E) relative to the optical imaging device (13, 14; 113, 114).

21. The device (1; 100) according to any one of claims 1 to 20, characterized in that The device (1; 100) comprises an ophthalmic microscope (150) having a microscope focal length (f) which is in particular the same as the focal length (f) of the optical imaging device (13, 14; 113, 114).

22. An ophthalmic instrument (150A) for treating an eye (4; 104) of a patient, comprising an ophthalmic microscope (150), characterized in that Apparatus (1; 100) according to any one of the preceding claims.

23. A method for operating a device (1; 100), in particular for operating a device (1; 100) according to one of claims 1 to 21, for determining a position (2; 102) of an object of interest (3; 103) in an eye (4; 104) of a patient, in particular in the vitreous body (5; 105) of the eye (4; 104), wherein: At least two optical paths (11, 12; 111, 112) cross each other at a common intersection point (F) through a reference plane (Y), wherein each of the at least two optical paths (11, 12; 111, 112) images the intersection point (F) or a vicinity thereof as spaced-apart images (O1, O2; O'1, O'2) at the reference plane (Y), and wherein the intersection point (F) and the reference plane (Y) are shifted relative to each other, whereby the images (O1, O2; O'1, O'2) are shifted relative to each other at the reference plane (Y), and an original distance (C) from the intersection point (F) to the reference plane (Y) is determined by the amount of these image shifts.

24. The method according to claim 23, characterized in that The at least two beam paths (11, 12; 111, 112) form a viewing angle (θ) with respect to each other.

25. A method for operating a device (1; 100), in particular for operating a device (1; 100) according to one of claims 1 to 21, for determining a position (2; 102) of an object of interest (3; 103) in an eye (4; 104) of a patient, in particular in the vitreous body (5; 105) of the eye (4; 104), wherein: A reference plane (Y) is generated which is orthogonal to a measuring axis (6; 106) of the device (1; 100); 100), wherein at least one light beam path (11, 12; 111, 112) passing through the reference plane (Y) intersects the measuring axis (6; 106) at a common intersection point (F), and wherein at least one light beam path (11, 12; 111, 112) generates a mark (27, 28; 127, 128) at the point of intersection at the reference plane (Y) so as to determine a distance (C) between the intersection point (F) and the reference plane (Y) at the reference plane (Y).

26. The method according to claim 25, characterized in that Additional markings (27, 28; 127, 128) are generated at the reference plane (Y).

27. The method according to any one of claims 23 to 26, characterized in that The beam paths (11, 12; 111, 112) are generated sequentially in a time-shifted manner.

28. The method according to claim 27, characterized in that The beam paths (11, 12; 111, 112) generated in a time-shifted manner are also generated in a position-shifted manner and form an imaginary observation angle with respect to one another.

29. The method according to claims 23 to 28, characterized in that A focal plane (E) is defined at the intersection point (F) of the two intersecting beam paths (11, 12; 111, 112).

30. The method according to claims 23 to 29, characterized in that The reference plane (Y) is established by at least one camera unit (15, 16; 115, 116).

31. A method for determining a position (2; 102) of an object of interest (3; 103) in an eye (4; 104) of a patient, in particular in the vitreous body (5; 105) of said eye (4; 104), wherein: An object distance (C) between the object of interest (3; 103) and the reference structure (23; 123) is determined at a reference plane (Y) defined by a known reference structure (23; 123) of the eye (4; 104).

32. The method according to any one of claims 23 to 31, characterized in that The distance, in particular the object distance (C), is determined by the ratio of the sides of a right triangle (156).

33. A method for determining a position (2; 102) of an object of interest (3; 103) in an eye (4; 104) of a patient, in particular in the vitreous body (5; 105) of said eye (4; 104), wherein: The object of interest (3; 103) is arranged in or near a generated focal plane (E), wherein a known anatomical eye structure (22; 122) of the eye (4; 104) is arranged in a generated reference plane (Y), wherein at least two optical paths (11, 12; 111, 112) passing through the reference plane (Y) are focused at or near the focal plane (E), wherein one or more image shifts of at least one image (O) focused relative to the focal plane (E) are determined at the reference plane (Y) when the focal plane (E) and the reference plane (Y) are moved relative to each other, and wherein a distance (C) between the focal plane (E) and the reference plane (Y) is determined at the reference plane (Y) by means of the image shifts.

34. A method for determining a position (2; 102) of an object of interest (3; 103) in an eye (4; 104) of a patient, in particular in the vitreous body (5; 105) of said eye (4; 104), wherein: The object of interest (3; 103) is arranged in or near a generated focal plane (E), wherein known anatomical eye structures (22; 122) of the eye (4; 104) are arranged in a generated reference plane (Y), wherein the known anatomical eye structures (22; 122) of the eye (4; 104) are arranged in the generated reference plane (Y), wherein at least one beam path (11, 12; 111, 112) passing through the reference plane (Y) is focused at or near the focal plane (E), and wherein a distance segment (B) between two marks generated by the at least one beam path (11, 12; 111, 112) at the reference plane (Y) is determined, and wherein a distance (C) between the focal plane (E) and the reference plane (Y) is determined at the reference plane (Y) by the determined distance segment (B).

35. The method according to any one of claims 23 to 34, characterized in that The determined object distance (C) is provided for operating the treatment machine in an automatic manner.

Images