KR101510721B1 - An ophthalmic surgical apparatus, an method for controlling thereof and method for surgery using that - Google Patents

Abstract

The present invention relates to an ophthalmic surgical apparatus, a control method thereof, and a surgical method using the same, the apparatus comprising: first image means for generating a first image of an anterior ocular segment; second image means for generating a second image of the anterior segment; A processor for generating a third image by correcting the first image using the shape information of the front eye part obtained from the second image and a laser system for irradiating the laser with the coordinates set based on the third image An ophthalmologic surgical apparatus including the same, a control method thereof, and a surgical method using the same.

Description

[0001] The present invention relates to an ophthalmic surgical apparatus, an ophthalmic surgical apparatus, a control method thereof, and a surgical method using the same,

The present invention relates to an ophthalmic surgery device, a control method thereof, and a surgical method using the same, and more particularly, to an ophthalmic surgery device capable of performing an anterior segment surgery using a femtosecond laser, a control method thereof, .

Cataract is a disease in which the crystalline lens of the eye becomes blurred and vision declines. If only the edge of the lens is turbid, it does not affect the visual acuity. However, when the lens core becomes turbid, various symptoms such as decreased vision, diplopia, and glare appear. Treatment of cataracts is mainly through surgery to remove opacified lenses and replace them with intraocular lenses, and cataract surgery is one of the most common operations.

In previous cataract surgery, the cornea was incised using a knife, and the anterior chamber of the lens was cut through the incision in a circular shape. Then, the lens nucleus was finely pulverized using ultrasonic waves and aspirated, , And an intraocular lens is inserted into the region where the nucleus of the lens is located. Such cataract surgery methods are similarly disclosed in Korean Patent Laid-Open Publication No. 1990-0015698.

However, since the conventional cataract surgery is performed manually by the operator by cutting the anterior capsule of the cornea and the lens and grinding the lens nucleus, it is difficult to grasp the time axis of the patient, incise the correct position, and insert the intraocular lens Respectively.

Recently, in order to solve these problems, there have been proposed surgical methods for incising a lens using a laser, and techniques for irradiating a laser at a desired position have been studied. However, in this case, Therefore, there is a problem that some errors occur.

Korean Patent Laid-Open Publication No. 1990-0015698

SUMMARY OF THE INVENTION The present invention is directed to provide an ophthalmic surgical apparatus, a control method thereof, and a surgical method using the apparatus, which can design a surgical operation by grasping a precise position of a patient.

In order to achieve the object of the present invention described above, the present invention provides an image processing apparatus comprising first image means for generating a first image of anterior segment, second image means for generating a second image of the anterior portion, A processor for correcting the first image to generate a third image using the shape information of the front eye part obtained from the first image and a laser system for irradiating the laser with the coordinates set based on the third image, A surgical device is provided.

Here, the first image means may generate an image using the OCT method, the second image means may generate an image using ultrasonic waves, the first image may not include the shape information of the lens tip of the anterior segment , And the second image may include shape information of the lens tip of the front eye part.

Thus, the processor is capable of using the shape information of the lens end obtained from the second image to generate the third image that completes the shape of the lens end in the first image. By using this, it is possible to determine the time axis of the front portion.

On the other hand, the above-described object of the present invention is also achieved by a method of producing a stereoscopic image, comprising the steps of generating a first image of a front eye using first image means, generating a second image of a front eye using second image means, Generating a third image by correcting the first image using the obtained shape information of the anterior ocular segment and setting coordinates of the laser to be irradiated to the anterior ocular segment based on the third image And a control method of the ophthalmic surgical apparatus.

Here, the generating of the first image may generate the first image using a tomographic image obtained by the OCT method, and the step of generating the second image may generate the second image using ultrasonic waves .

Since the step of generating the first image does not include the shape information of the lens end of the front eye part and the step of generating the second image includes the shape information of the lens end part of the front eye part, 3 image, the shape information of the lens end obtained in the second image based on the first image may be further corrected to generate the third image.

Then, it is possible to determine the time axis using the positions of both side ends of the lens obtained from the third image.

Furthermore, it is an object of the present invention to provide a method and an apparatus for acquiring an image of a subject, comprising the steps of generating a first image of the anterior segment using first image means, generating a second image of the anterior segment using the second image means, A step of correcting the first image to generate a third image using the shape information of the front eye part, and setting coordinates of the laser to be irradiated on the front part based on the third image It can also be achieved by the operation method of the eye.

Here, the step of generating the first image may generate the first image using the tomographic image obtained by the OCT method, and the step of generating the second image may generate the second image using ultrasonic waves.

The generating of the third image may further generate the third image by further correcting the shape information of the lens end obtained in the second image based on the first image. In the step of setting the coordinates of the laser, it is possible to set the time axis using the position of both ends of the lens of the anterior part, and to perform the operation.

According to the present invention, since it is possible to acquire an image of the entire lens and set a time axis, it is possible to improve the effect of the surgery by setting the optimum position for surgery.

1 is a block diagram schematically showing the configuration of an ophthalmic surgical apparatus according to a first embodiment of the present invention.
FIG. 2 is a flowchart showing an ophthalmic operation method using the ophthalmic surgery apparatus of FIG. 1 and a control method of the surgical apparatus corresponding thereto;
FIG. 3 is a view showing a treatment part according to the surgical step of FIG. 2,
FIG. 4 is a flow chart showing in detail the process of the diagnosis and setting step of FIG. 2,
5 shows a tomographic image taken by an OCT section,
6 is a cross-sectional image taken by the ultrasound imaging unit,
FIG. 7 is a view showing a state in which the axis of the lens is determined in FIG. 4,
8 is a block diagram schematically showing a configuration of an ophthalmic surgery apparatus according to a second embodiment of the present invention,
FIG. 9 is a flowchart showing the details of the diagnosis and setting step according to the second embodiment.

Hereinafter, an ophthalmic surgical apparatus using a laser, a control method thereof, and an ophthalmic surgery method using the same according to an embodiment of the present invention will be described in detail with reference to the drawings. In the following description, the positional relationship of each component is principally described based on the drawings. The drawings may be simplified for simplicity of the description or exaggerated when necessary. Therefore, the present invention is not limited thereto, and it is needless to say that various devices may be added, changed or omitted.

1 is a block diagram schematically showing a configuration of an ophthalmic surgery apparatus according to a first embodiment of the present invention. As shown in Fig. 1, the ophthalmic surgical apparatus comprises a laser system 100 for processing and delivering a therapeutic laser and a light source for generating a therapeutic laser. Here, the laser system may be configured to include a light converting unit and a light transmitting unit.

The light source 110 comprises at least one or more resonance stages (not shown), and generates a therapeutic laser for use in ophthalmic surgery. The laser generated in the light source 110 may be a microwave laser having a pulse duration of 10 to 10,000 femtoseconds. These microwave femtosecond lasers are capable of precise treatment at the cellular level and have the advantage of minimizing the effects on the cells located adjacent to the treatment site and allowing them to operate.

The light source 110 of this embodiment has a wavelength of 1000 nm to 1100 nm and is configured to generate a laser having a pulse frequency of 10 KHz to 500 KHz. However, it is also possible to use a laser having a wavelength or a pulse frequency other than the above range as an example.

The light-converting unit 120 includes a plurality of optical elements capable of changing laser parameters. Here, the parameter of the laser may be understood to mean the output of the laser, the waveform of the pulse, the irradiation time, the irradiation diameter, and the like. Accordingly, the laser generated by the light source 110 is processed while passing through the light conversion unit 120, and is adjusted to a shape suitable for anterior segment surgery.

Although not shown in the drawings, the light converting unit 120 may include a half wave plate and a linear polarizer to convert laser output and polarization characteristics of the laser. At this time, it is possible to precisely control the output and polarization characteristics of the laser by feedback control by providing a separate detector.

The optical conversion unit 120 may be configured to sequentially array various optical elements capable of adjusting parameters such as the diameter, divergence, and astigmatism of the laser, Lt; / RTI > However, since these elements are widely used in other optical devices, a detailed description thereof will be omitted.

The light conversion unit 120 also includes a plurality of optical elements including a plurality of lenses, mirrors, and splitters. Accordingly, the laser generated in the light source 110 flows into one end, and the light path of the laser irradiated to the treatment region is formed through the light irradiation portion formed at the other end.

The light converting unit 120 is configured to be able to vary the optical path so as to change the irradiating position of the laser irradiated through the light irradiating unit. Therefore, by driving the optical element constituting the light converting unit 120, the laser can be irradiated to various positions of the frontal part.

Specifically, the light converting unit 120 includes an X-Y scanner (not shown) and a Z scanner (not shown). Here, the X-Y scanner includes at least two galvano mirrors, and the irradiation position of the laser on the horizontal plane can be adjusted by driving the X-Y scanner. The Z scanner includes at least one or more lenses movable along the traveling direction of the laser, and the depth to which the laser is irradiated is determined by driving the Z scanner. Therefore, as the laser passes through the light converting unit 120, the irradiating position can be changed variously in the horizontal direction and the vertical direction (refer to FIG. 1).

As described above, cataract surgery requires treatment at various sites such as the cornea, the anterior capsule of the lens, and the nucleus of the lens. Therefore, the optical transmission unit according to the present embodiment can control the X-Y scanner and the Z scanner to irradiate various positions of the anterior part with laser to proceed the surgery.

In FIG. 1, the light-converting unit and the light-transmitting unit are shown as separate blocks, but they are merely shown separately for convenience in explaining the function of the optical element through which the laser passes. In constructing the embodiment, it is also possible to perform both the functions of the optical converting unit and the optical transmitting unit by forming the optical path of the optical element for converting the parameter of the laser. In the drawings, the light conversion portion is disposed forward in the traveling direction of the laser and the light transmission portion is disposed at the rear, but the present invention is not limited to this order, and the optical element and the light transmission portion constituting the light conversion portion And it is possible to arrange them in various arrangements by mixing optical elements to be constituted.

As described above, the laser generated in the light source 110 passes through the light conversion unit 120 and the light conversion unit 120 and is irradiated to the outside through the light irradiation unit. At this time, the light irradiating unit includes an objective lens, and the objective lens can be installed so as to be movable along the traveling direction of the laser. The light irradiated through the light irradiating unit can be irradiated to the anterior segment of the patient for treatment.

At this time, the eye of the patient is fixed in a suction state by the eye interface 600 so as to maintain the fixed state. The eye interface 600 may be integrally provided at the rear of the objective lens (on the basis of the advancing direction of the laser), or may be constituted by a separate member and may be configured to be coupled to the distal end of the light- have.

Meanwhile, the ophthalmic surgery apparatus according to the present embodiment further includes an image detection unit for obtaining an image of the anterior segment in which surgery is performed. The image detecting unit 200 may include a camera unit 210, an optical coherence tomography (OCT) unit 200, and an ultrasound imaging unit 230.

The camera unit 210 is a device capable of acquiring a two-dimensional image of the eye surface. The camera unit 210 includes a separate camera light source (not shown), and detects an image using a camera light source. 1, the camera light is irradiated by a beam combiner of the light converting unit 120 described above, and is incident on the eye interface (not shown) 600). ≪ / RTI > It is possible to detect the light reflected from the surface of the eye and obtain a two-dimensional image of the surface of the eye.

The OCT unit 220 is a device capable of obtaining a cross-sectional image of the anterior segment. Optical coherence tomography (OCT) is a technique for obtaining a tomographic image using light interference and is widely used as a noninvasive diagnostic method because of its superior resolution compared to computed tomography (CT). In recent years, a technique has been developed for acquiring a three-dimensional image by processing a plurality of tomographic images at a very high speed. In this embodiment, the OCT capable of acquiring three- It is possible to acquire an image.

However, since the OCT unit 220 acquires an image using the interference phenomenon of light using light, it is difficult to acquire an image of a region where the light is not irradiated. For example, a region located on the lower side of the pupil of the lens located inside the anterior portion can be irradiated with light, thereby securing an image through the OCT portion 220. However, There is a disadvantage in that an image can not be secured through the OCT unit 220 (see FIG. 5).

Therefore, in the present embodiment, the ultrasonic imaging unit 230 for securing an image of the inside of the anterior segment may be further included. The ultrasound imaging unit 230 is also an apparatus that can acquire a cross-sectional image of the anterior segment. The ultrasound imaging unit 230 irradiates ultrasound with eyes and acquires a tomographic image using a pattern of ultrasonic waves reflected from each tissue. Since the ultrasound imaging unit 230 utilizes ultrasound rather than light, it can acquire images of areas where light can not pass through, and is widely used in the field of medical diagnostic equipment. In recent years, a technology has been developed to acquire three-dimensional images by processing a plurality of tomographic images obtained by ultrasonic imaging at an ultra-high speed. In this embodiment, an ultrasound imaging unit capable of acquiring three- , In particular, the image of the crystalline body (see Fig. 6).

The ultrasound imaging unit 230 is installed to be in contact with the anterior segment so as to transmit ultrasonic waves in a state of being in contact with the anterior segment of the patient. In this embodiment, a transmission module for transmitting ultrasonic waves to the contact surface of the eye interface 600 for fixing the eyes of the patient and a sensing module for sensing the reflected ultrasonic waves may be provided. However, it is also possible that the ultrasonic imaging unit is not a structure formed integrally with the eye interface, but may be constituted by a separate member. For example, the ultrasound imaging unit may be configured as a member that can be installed along the outer periphery of the eye interface in a state where the ultrasound imaging unit is fixed to the eye interface. The ultrasound imaging unit may include a separate probe type member, It is also possible to transmit ultrasound in a state and detect the reflected information.

The image obtained by the ultrasound imaging unit 230 has a disadvantage in that resolution is lowered as compared with an image obtained by the OCT unit 220. However, the advantage of being able to capture a region that can not be acquired by the OCT unit 220 In this embodiment, information provided from the OCT unit 220 and the ultrasound imaging unit 230 can be supplemented and used. However, the detailed description of the camera unit, the OCT unit, and the ultrasound imaging unit of the image detection unit is a technology widely used in the similar technical field, and therefore, a detailed description of the structure will be omitted.

The surface image and the tomographic image of the eye obtained in the image detecting unit 200 may be processed by the processor 300 and provided to the interface 500. The interface 500, including the display, can display the image obtained in the image detecting unit 200. [ The image displayed through the interface 500 can be used for various purposes.

For example, it is possible to check whether the eye is normally docked by providing an image of a patient's eye fixed on the eye interface 600 transmitted from the camera unit 210. It is also possible to select a site where the cornea is incised, It can be used to mark areas.

Further, the tomographic image of the anterior segment transmitted from the OCT unit 220 can be provided as data for diagnosing the inside of the anterior segment of the patient, and can be provided as image data that can be referred to when selecting the incision range and pattern of the lens . The three-dimensional image obtained by processing the images of the OCT unit 220 and the ultrasound radiographing unit 230 can be used to calculate the optical axis and coordinates to be irradiated with the laser. Providing images can be utilized.

In this way, the interface 500 can be used variously to obtain information about the surgical site, design the surgery, and display the surgical procedure by using the information obtained from the image detector 200.

Further, the interface 500 is configured so that the user can perform various operations including driving the surgical apparatus. Accordingly, the user can input various commands by referring to the images and images displayed on the display, such as selection of an operation position, design of operation contents, patient information viewing, and the like. The interface 500 according to the present embodiment may be configured as a touch screen so that a user can select various contents by using an image to be displayed, but the present invention can be configured in various other ways as well.

Meanwhile, the processor 300 may process the image data acquired from the image detector 200 and provide the processed image data to the interface 500. For example, a three-dimensional image of the anterior segment may be constructed and provided to the interface 500 using the tomogram data acquired by the OCT unit 220, or a cross-sectional image of a specific direction requested by the interface 500 may be extracted, (500).

In addition, the processor 300 may perform various calculations using image data and coordinate data. For example, the processor 300 calculates the coordinates between the surface image of the eye obtained at the camera unit, the tomographic image acquired at the OCT unit 220, and the three-dimensional image obtained from the tomographic image, You can perform the task of matching the relationship. Accordingly, when the user selects a specific position of the surface of the eye through the interface 500, it is possible to provide a tomographic image and three-dimensional image data corresponding to the position. In addition, when the user selects a position or sets a surgical site through the displayed image, it is possible to provide an image of the corresponding coordinates or to calculate coordinates to be irradiated with the laser by calculating the coordinates with the coordinates.

Further, the processor 300 of the present embodiment can process the three-dimensional image obtained by the OCT unit 220 and the three-dimensional image obtained by the ultrasound imaging unit 230, thereby accurately setting the time axis of the patient's eye. However, these functions will be described in more detail below.

In addition, the processor 300 may perform a function of processing internally obtained data and externally input data. However, since the functions of these processors are widely used in the industrial field, a description of general functions is omitted.

The controller 400 may include a light source 110, a light converting unit 120, and a light transmitting unit 120. The light source 110 may emit a laser beam at a corresponding position according to a user's input through the interface 500, (130). ≪ / RTI >

For example, the control unit 400 controls various components of the light source 110 and the light conversion unit 120 to generate a laser used for surgery, and generates a pulse waveform, an output, Various parameters such as size can be adjusted. In addition, it is possible to control various components of the light transmitting part according to the pattern designated by the user or the predetermined operation mode, to control the laser to be irradiated on the set treatment area, and to adjust the locus and the pattern to be irradiated with the laser. Further, when an abnormality occurs during operation of the surgical apparatus, it is also possible to operate a shutter (not shown) provided in the light converting unit 120 to block the irradiation of the laser with eyes.

In addition, the control unit 400 can control the operation of various components even in the step of fixing the eyes of the patient performed before the surgery and the step of confirming the operation result after the operation.

As described above, according to the ophthalmic surgery apparatus using the laser according to the present embodiment, it is possible to treat various parts of the anterior part by using a laser. At this time, by using various images obtained from the image detecting part 200 It is possible to easily design the surgery and to carry out the operation.

Hereinafter, a method of operating the cataract using the above-described ophthalmic surgery apparatus and a control method of the surgical apparatus corresponding thereto will be described in detail.

FIG. 2 is a flowchart illustrating an ophthalmic surgical method using the ophthalmic surgery apparatus of FIG. 1 and a control method of the surgical apparatus corresponding thereto, and FIG. 3 is a view illustrating a treatment site according to the surgical procedure of FIG. In FIG. 2, the left side shows each surgical stage, and the right side shows a control stage of the anterior segment surgery apparatus corresponding to each surgical stage.

As shown in FIG. 2, when the patient is positioned in the ophthalmic surgical apparatus, a step of fixing the eyes of the patient is performed (S10, S100). In this step, the patient's eyes are sucked using the eye interface 600 while the patient is lying on the bed, and then the end of the light irradiation part of the surgical apparatus is lowered and the eye interface 600 is docked to the end .

However, in the present embodiment, the structure using the eye interface separate from the ophthalmic surgery device is mainly described, but the eye interface may be integrally formed at the end of the light irradiation part so that the position of the light irradiation part may be lowered to proceed with the docking step Do.

As described above, the step of fixing the eye of the patient can proceed with docking while continuously referring to the image obtained through the image detector 200 so that the center of the optical path and the time axis of the eye are aligned.

When the position of the patient's eyes is fixed, a step of diagnosing the patient's eyes and setting the operation contents is performed (S20, S200). In this step, the image information can be provided through the interface 500 so as to utilize the surface image of the eye, the anterior segment tomographic image, the three-dimensional image of the lens, etc. obtained by the image detecting unit 200. Accordingly, the user can set specific surgical information such as the incision position, the laser parameter, and the pattern of the cornea and the lens using the information of the patient collected in the pre-operation stage and various image information provided through the interface 500 .

When the operation area is set by the user's selection, the processor 300 can calculate the coordinates of the area and provide the calculated coordinates to the controller 400. Accordingly, the control unit 400 can control the driving of the laser system 100 using the coordinates provided by the processor 300. [

Further, in this step, the processor 300 may include determining the time axis of the patient using the anterior segment image provided. The patient 's visual axis is an important factor to be considered in setting the surgical area, and can have a large effect on the surgical outcome. Therefore, the processor 300 according to the present embodiment determines an accurate time axis by using the images provided by the OCT unit 220 and the ultrasound imaging unit 230, sets the operation region, and selects coordinates It is possible to provide.

However, specific procedures for determining such time axis will be described in detail below using separate drawings.

When the setting of the operation contents is completed, a capsulotomy is performed (S30, S300) in which the anterior capsule of the lens is circularly cut. The circular anterior capsular incision is performed by cutting the front surface (see B in Fig. 3A) of the capsule-shaped lens, thereby preventing the lens pressure from increasing during incision of the lens core region The patient was treated with an intraocular lens. At this time, the locus irradiated with the laser beam at the anterior capsule incision can be configured to form a concentric circle centering on the time axis. Or may be configured to form an elliptical trajectory according to the shape of the lens to be inserted. However, it is desirable to design the coordinates so that the time axis passes through the center of the locus where the laser is irradiated during the anterior capsule incision. Therefore, when the IOL is inserted in the future, the intraocular lens is positioned to have the same axis as the removed lens, and the surgical effect can be improved. In order to perform this step, the ophthalmic surgical apparatus operates in the first operation mode, and irradiates the laser along the locus set on the front surface of the lens to circularly cut the anterior capsule (see P1 in Fig. 3B).

When the circular anterior capsular incision step is performed, a step of cutting the nucleus region of the lens (see B in FIG. 3A) is performed (S40, S400). The incision of the nucleus site is performed by incising the cloudy part of the cataract. The cataract-hardened nucleus is cut or softened with a laser using a laser to easily remove the lens nucleus through the inhalation process in the future It is possible to do.

At this time, if the posterior chamber of the lens (see D in FIG. 3A) is damaged while the nucleus of the lens is removed, the incisional lens piece is transferred to the vitreous body (see E in FIG. 3A) Lt; / RTI > Therefore, in setting the laser irradiation area, it is necessary to secure a safety distance from the posterior capsule so that the posterior capsule of the lens is not damaged in the course of this step.

To perform this step, the ophthalmic surgical device operates in a second mode of operation and irradiates the laser to the nucleus of the lens. In this embodiment, the laser is set to be irradiated with a trapezoidal locus (see P2 in FIG. 3A), but this is only an example, and laser traces can be formed in various shapes so as to cut the lens into small pieces.

In addition, since this step cuts a nucleus portion having a predetermined thickness unlike the anterior capsular incision and corneal incision, the laser is not irradiated on one plane, but the Z scanner operates and incisions are made in a plurality of layers having different depths . At this time, the trajectories irradiated with the laser beams in the respective layers may be irradiated with the same trajectory, and they may be configured to form different trajectories for respective layers so as to facilitate the incision of the lens.

Further, when the laser is irradiated to the tissue, air bubbles are generated. When the laser is irradiated at various depths as in this step, the laser is scattered by the bubbles generated by the preceding laser, A case may arise. Therefore, in the operation of the ophthalmic surgical apparatus, the irradiation of the laser in the second operation step first irradiates the portion adjacent to the posterior capsule of the lens, and the position adjacent to the anterior portion of the capsule is examined later to minimize the influence of the air bubbles generated by the preceding laser have.

When the incision of the lens is completed, a step of cutting the cornea (see A in Fig. 3A) is performed (S50, S500). The corneal incision is a step of incising a predetermined section of the cornea so as to form a passage into which the suction device can be inserted. In addition, in order to improve the astigmatism due to corneal aneurism at the same time as cataract surgery, it is possible to simultaneously perform a procedure of changing the shape of the cornea by cutting a specific portion of the cornea.

To perform this step, the ophthalmic surgical apparatus operates in a third mode of operation and irradiates the laser to a predetermined area of the cornea (see P3 in Fig. 3B). At this time, the area where the cornea is incised can be set through a user interface by referring to the result of the cornea test measured before the surgery.

When the front of the lens, the nucleus of the lens and the corneal incision are completed through the laser irradiation, the ophthalmic surgical apparatus releases the docking state and removes the eye interface from the patient's eye (S600).

In addition, by inserting the probe-type suction device into the incision site of the cornea and sucking the incised incision lens, it is possible to completely remove the lens except the posterior capsule of the lens (S60). The cataract surgery can be completed by inserting the intraocular lens at the position where the lens is removed (S70).

As described above, the above-described ophthalmic surgery device advances the operation of cutting the anterior capsule, crushing the lens, and incising the cornea in such a manner that the laser is irradiated, so that it is possible to obtain faster and more accurate accuracy than in the conventional art .

Hereinafter, the procedure of setting the time axis in the diagnosis and setting step of FIG. 2 will be described in more detail with reference to FIG. 4 to FIG.

As described above, since the time axis of the patient is directly related to the setting of the surgical site and the insertion position of the intraocular lens, precise setting of the time axis greatly affects the visual acuity of the patient after the surgery. In the past, the procedure was performed assuming that the axis of the axis coincided with the center of the pupil, but the axis of the axis and the center of the pupil do not coincide with each other depending on individual characteristics. In addition, even if the shape of the lens is determined by using OCT, since the position of the end of the lens located at the lower side of the iris can not be photographed, the surface of the obtained image is extended to virtually grasp the shape of the end of the lens I could not help it. Therefore, even if OCT is used, there is a limit to setting an accurate time axis. Accordingly, the present embodiment provides an apparatus and method for accurately determining the time axis by simultaneously providing the OCT unit 220 and the ultrasound imaging unit 230.

FIG. 4 is a flowchart showing details of the diagnostic and setting step of FIG. As described above, the diagnostic and setting step is a process of diagnosing the condition of the patient and setting the operation contents using the patient information collected in the pre-operation step and various image information provided through the interface unit. This paper focuses on the steps that are relevant to setting.

First, the diagnosis and setting step may include obtaining a first image (S210). In the first image acquiring step, a tomographic image of the inside of the anterior segment is photographed using the OCT unit 220. Then, the processor 300 generates a three-dimensional first image using the tomographic image.

5 is a tomographic image taken by the OCT section. As shown in FIG. 5, the tomographic image obtained using the OCT unit 220 provides a high resolution image in the center region of the lens, but the end of the lens located below the iris can not be irradiated with light Obtaining an image is unclear. Therefore, when such a tomographic image is processed to generate a first image, both ends of the lens acquire an unclear three-dimensional image.

Therefore, in this embodiment, the step of acquiring the second image is performed together (S220). In the second image acquisition step, the tomographic image of the inside of the anterior segment is photographed using the ultrasound imaging unit 230. The processor then processes the tomographic image to generate a second image in three dimensions.

6 is a tomographic image taken by the ultrasonic imaging unit. Since the tomographic image obtained using the ultrasound imaging unit 230 uses a sound wave, it is possible to acquire morphological information of a position where the resolution is low but the light is not irradiated. Therefore, as shown in FIG. 6, it is possible to accurately grasp the shape of the end portion of the lens, unlike the tomographic image taken by the OCT portion 220. Thus, the processor 300 can process it to create a three-dimensional image that includes the shape of the end of the lens.

Once the first image and the second image are generated, the processor 300 proceeds to generate a third image. As described above, the first image has a high resolution but the shape of the lens end is not clear, and the second image has a low resolution, but clearly shows the shape information of the end portion of the lens. Thus, the processor 300 generates the third image in a manner that adds the shape of the lens end to the first image, using the shape information of the lens end shown in the second image. Thus, the third image can clearly represent a three-dimensional image of the overall shape of the lens.

However, in the above description, a three-dimensional image is generated using the OCT unit, a three-dimensional image is generated using the ultrasonic imaging unit, and a complete three-dimensional image of the lens is derived therefrom. The process of generating the third image by processing the image information obtained from the OCT unit and the information obtained through the ultrasound imaging unit can be implemented in various ways.

On the other hand, if the third image is generated as described above, it is possible to determine the time axis based on the generated third image (S240). The lens is composed of a lens, and the axis of the lens is generally passed through the center of the lens. Accordingly, as shown in FIG. 7, a pair of points corresponding to both end portions of the lens are connected (L1) in the third image, and a pair of points corresponding to both end portions of the lens are connected in the other direction L1), it is possible to determine the optical axis so that the intersection O is determined as the center of the lens and penetrate the lens.

However, the method used in FIG. 7 is one method of determining the time axis of a normal-shaped lens, and it is also possible to set the time axis in another manner using the three-dimensional shape of the lens.

When the time axis is determined, a step of designing a position where light is irradiated is performed (S250). The selection of the irradiation position can be performed considering the time axis. Specifically, it is preferable that the position where the anterior capsule of the lens is incised and the cross-section where the core part of the lens is incised are designed to be symmetrical with respect to the axis of the axis. As an example, FIG. 7 shows a state in which the locus irradiated with the laser beam at the anterior capsule incision stage of the lens is designed to form a concentric circle around a predetermined axis (P1). In this case, a circular sac is formed around the time axis, and since the intraocular lens is located in the circular sac in the future, the same time axis as that of the pre-operative time axis is formed, thereby maximizing the surgical effect.

Hereinafter, an ophthalmic surgical apparatus according to a second preferred embodiment of the present invention, a control method thereof, and a surgical method using the same will be described. However, the same or similar components as those of the first embodiment will not be described in order to avoid redundancy.

In the first embodiment, the ophthalmologic surgical apparatus is provided with an ultrasound imaging unit. However, the ultrasound imaging unit may be configured not to have the ultrasound imaging unit itself but to use the ultrasound imaging image captured by other equipment.

FIG. 8 is a block diagram schematically showing a configuration of an ophthalmic surgery apparatus according to a second embodiment of the present invention, and FIG. 9 is a flowchart illustrating details of a diagnosis and setting step according to the second embodiment.

As shown in FIG. 8, the image detecting unit of the ophthalmic surgery apparatus according to the present embodiment includes a camera unit and an OCT unit, and may not include an ultrasound imaging unit. Instead, a second image photographed through a separate ultrasound imaging apparatus may be provided in the form of data before proceeding to surgery. Here, the second image provided from the outside may be an image including shape information of the end of the lens as in the above-described embodiment.

On the other hand, the processor of the above-described embodiment generates the third image using the first image and the second image obtained from the image detecting unit, whereas the processor according to the present embodiment uses the first image obtained from the image detecting unit, And to generate a third image using a second image obtained from the information.

The third image is used to determine the time axis of the patient, and the laser irradiation area can be set during the operation. Since the above description has been described in detail in the above embodiments, detailed description will be omitted.

This embodiment follows the same steps as the surgical procedure shown in Fig. 2 and the control step of the surgical apparatus, as in the above-described embodiment. However, as shown in FIG. 9, instead of generating the second image using the ultrasound imaging unit provided in the system, the second image is generated by receiving information photographed from the outside (S220).

9, the first image is generated and the second image is received from the outside. However, the present invention is not limited to the order of the steps. For example, It is also possible to proceed before the image generation step, and it goes without saying that the docking is performed and the patient's eye is fixed before the eye is fixed.

As in the above-described embodiment, the processor can generate the third image, determine the time axis, and proceed the remaining steps to effectively perform the operation.

As described above, according to the first and second embodiments described above, the operation can be performed by setting the time axis in consideration of the overall shape of the lens of the patient, thereby remarkably improving the effect of the surgery. Further, even in the case of a patient having a lens having a specific shape, since it is possible to set the optimal position of the surgical operation by analyzing the entire shape of the lens, it is possible to establish an optimal surgical plan considering the individual characteristics of the patient.

Further, according to the second embodiment, it is possible to utilize the ultrasonic imaging image photographed in the pre-examination step without using a separate ultrasonic imaging unit, so that the operation can be simplified and the device can be more compact There is an advantage that it can be configured.

100: laser system 200: image detector
210: camera part 220: OCT part
300: processor 400:
500: Interface

Claims (26)

First imaging means for generating a first image of the lens;
Second image means for generating a second image including a shape around the lens;
A processor for correcting the first image to generate a third image using the shape information about the lens acquired from the second image; And
And a laser system for irradiating the laser with the coordinates set based on the set time axis using the shape information of the periphery of the lens of the third image. The method according to claim 1,
Characterized in that said first image means is capable of obtaining an image of higher resolution than said second image means and said second image means is capable of obtaining image information of a region which is not produced by said first image means Ophthalmic surgical apparatus. The method according to claim 1,
Wherein the first image and the second image are three-dimensional images. The method according to claim 1,
Wherein the first image means generates an image using an OCT method, and the second image means generates an image using ultrasonic waves. delete The method according to claim 1,
Wherein the processor uses the shape information of the lens end obtained from the second image to generate the third image that completes the shape of the lens end in the first image. The method according to claim 1,
Wherein the processor determines the time axis by using positions of both side ends of the lens. 8. The method of claim 7,
Wherein the processor sets a trajectory for irradiating a laser to the front of the lens, and the time axis passes through a center of a locus where the laser is irradiated to the frontal region. Receiving first image information of the lens from the first image means;
Receiving second image information including shape information about the lens from the second image means;
Correcting the first image to generate a third image using shape information about the lens acquired from the second image;
And determining a time axis of the lens using the shape information of the periphery of the lens of the third image. 10. The method of claim 9,
Characterized in that said first image means is capable of obtaining an image of higher resolution than said second image means and said second image means is capable of obtaining image information of a region which is not produced by said first image means Control method of ophthalmic surgical apparatus. 10. The method of claim 9,
Wherein the first image, the second image, and the third image are three-dimensional images. 10. The method of claim 9,
Wherein the step of generating the first image generates the first image using a tomographic image obtained by the OCT method and the step of generating the second image generates the second image using ultrasonic waves Control method of ophthalmic surgical apparatus. delete 13. The method of claim 12,
Wherein the generating of the third image further comprises correcting the shape information of the lens end portion obtained in the second image based on the first image to generate the third image. Way. 15. The method of claim 14,
Wherein the determining of the time axis determines a time axis using positions of both side ends of the lens obtained from the third image. delete delete delete delete delete First imaging means for generating a first image of the lens;
A processor for receiving a second image including a shape around the lens from the outside and correcting the first image using shape information about the lens obtained from the second image to generate a third image; And,
And a laser system for irradiating the laser with the coordinates set based on the set time axis using the shape information of the periphery of the lens of the third image. 22. The method of claim 21,
Wherein the first image is an image generated by an OCT method and the second image is an image generated by an ultrasound imaging. Receiving first image information of the lens from the first image means;
Receiving second image information including shape information about the lens from the outside;
Correcting the first image to generate a third image using shape information about the lens acquired from the second image; And,
And determining a time axis of the lens using the shape information of the periphery of the lens of the third image. 24. The method of claim 23,
Wherein the first image information is image information generated by an OCT method, and the second image information is image information generated by an ultrasound imaging. delete delete

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