Disclosed are a smart auxiliary diagnosis system and method for fundus oculi laser surgery, comprising a imaging stabilization and laser treatment device (1), a data control device (2), an image display device (3), and a data processing device (4); a first database (41) thereof stores fundus oculi image data; disease feature data in a fundus oculi image is extracted by means of a feature extraction module (42); a data analysis matching module (45) is used to perform a comparison operation, perform matching with disease feature data stored in a known-case feature template library (44), and store the result of the matching operation in a second database (43); if the degree of matching exceeds a set threshold, then a corresponding auxiliary diagnosis conclusion is provided, and an auxiliary diagnosis report is generated by means of a diagnosis report generation module (46).

The disclosure provides a system that may: determine first multiple focal point distances associated with respective multiple positions of a plane orthogonal to a laser beam; determine second multiple focal point distances associated with the respective multiple positions via for each position of the multiple positions: determine multiple intensity values associated with respective multiple interim focal point distances, each interim focal point distance greater than each focal point distance of the first multiple focal point distances associated with the position; determine an interim focal point distance respectively associated with a maximum intensity value; and determine a focal point distance as the interim focal point distance; and determine a depth of at least one incision in an eye based at least on differences between each of the second multiple focal point distances and each respective one of the first multiple focal point distances.

A laser surgery system includes a light source, an eye interface device, a scanning assembly, a confocal detection assembly and preferably a confocal bypass assembly. The light source generates an electromagnetic beam. The scanning assembly scans a focal point of the electromagnetic beam to different locations within the eye. An optical path propagates the electromagnetic beam from a light source to the focal point, and also propagates a portion of the electromagnetic beam reflected from the focal point location back along at least a portion of the optical path. The optical path includes an optical element associated with a confocal detection assembly that diverts a portion of the reflected electromagnetic radiation to a sensor. The sensor generates an intensity signal indicative of intensity the electromagnetic beam reflected from the focal point location. The confocal bypass assembly reversibly diverts the electromagnetic beam along a diversion optical path around the optical element.

The invention relates to a method for providing control data of an eye surgical laser (18). A control device (20) ascertains (S1) a lenticule geometry of a lenticule (12) to be separated from predetermined visual disorder data of a human or animal eye (36), wherein the lenticule geometry is defined by means of a refractive power value to be corrected and a lenticule diameter, ascertains (S2) a correction value for compensating for a deformation of the lenticule (12), which is generated by at least one contact element (28) of the treatment apparatus (10), wherein the correction value is determined by means of at least one preceding measurement of the treatment apparatus (10), ascertains (S3) a deformation geometry of the lenticule (12), wherein a deformation refractive power value is calculated depending on the refractive power value to be corrected and the correction value and a deformation diameter is calculated depending on the lenticule diameter and the correction value, and provides (S4) control data for controlling the eye surgical laser (18), which uses the deformation geometry for the separation of the lenticule (12).

The invention relates to a method for providing control data of an eye surgical laser (18). A control device (20) ascertains (51) a lenticule geometry of the lenticule (12) to be separated from predetermined visual disorder data of a human or animal eye (36), wherein the lenticule geometry is defined by means of a refractive power value to be corrected and a lenticule diameter, ascertains (S2) a correction value for compensating for a deformation of the lenticule (12), which is generated by at least one contact element (28) of the treatment apparatus (10), wherein the correction value is determined by means of at least one preceding measurement of the treatment apparatus (10), ascertains (S3) a deformation geometry of the lenticule (12), wherein the deformation geometry is defined by means of the refractive power value and a deformation diameter, wherein the deformation diameter is calculated depending on the lenticule diameter and the correction value, and provides (S4) control data for controlling the eye surgical laser (18), which uses the deformation geometry for the separation of the lenticule (12).

A device for defining a flap geometry of a flap for laser treatment of a human eye comprises a control unit programmed to evaluate ablation profile data of an ablation profile for a laser ablation treatment of a human cornea and to define the flap geometry based on this evaluation.

An initial treatment pattern defining an initial volume of ocular tissue to be modified for treating glaucoma is designed. An initial laser treatment is delivered by scanning a laser beam across ocular tissue at an initial placement in the eye in accordance with the initial treatment pattern to thereby photo disrupt the initial volume of ocular tissue. A postoperative measure of intraocular pressure (IOP) is evaluated relative to an IOP criterion to determine if the treatment was successful. If the treatment was not successful, meaning the IOP criterion was not satisfied, then a subsequent treatment pattern that defines a subsequent volume of ocular tissue to be modified, and/or a subsequent placement in the eye is determined. A subsequent laser treatment is delivered by scanning a laser beam across ocular tissue at the subsequent placement within the eye in accordance with the subsequent treatment pattern to thereby photo disrupt the subsequent volume of ocular tissue.

A laser eye surgery system that has a patient interface between the eye and the laser system relying on suction to hold the interface to the eye. The patient interface may be a liquid-filled interface, with liquid used as a transmission medium for the laser. During a laser procedure various inputs are monitored to detect a leak. The inputs may include a video feed of the eye looking for air bubbles in the liquid medium, the force sensors on the patient interface that detect patient movement, and vacuum sensors directly sensing the level of suction between the patient interface and the eye. The method may include combining three monitoring activities with a Bayesian algorithm that computes the probabilities of an imminent vacuum loss event.

In certain embodiments, a system for controlling a position of a focal point of a laser beam comprises a beam expander, a scanner, an objective lens, and a computer. The beam expander controls the focal point of the laser beam and includes a mirror and expander optical devices. The mirror has a surface curvature that can be adjusted to control a z-position of the focal point. The expander optical devices direct the laser beam towards the mirror and receive the laser beam reflected from the mirror. The scanner receives the laser beam from the beam expander and manipulates the laser beam to control an xy-position of the focal point. The objective lens receives the laser beam from the scanner and directs the beam towards the target. The computer receives a depth instruction, and sets actuation parameters to control the surface curvature of the mirror according to the depth instruction.

A method of generating three dimensional shapes for a cornea and lens, the method including illuminating an eye with multiple sections of light and obtaining multiple sectional images of the eye based on the multiple sections of light. For each obtained multiple sectional image, the following processes are performed: a) automatically identifying arcs corresponding to anterior and posterior corneal and lens surfaces of the eye by image analysis and curve fitting of the obtained multiple sectional images; and b) determining an intersection of lines ray traced back from the identified arcs with a known position of a section of space containing the section of light that generated the obtained multiple sectional images, wherein the intersection defines a three-dimensional arc curve. The method further including reconstructing three-dimensional shapes of the cornea surfaces and the lens surfaces based on fitting the three-dimensional arc curve to a three-dimensional shape.