KR101444757B1 - An ophthalmic surgical apparatus, an method for controlling thereof and method for surgery using that - Google Patents

Abstract

[0001] The present invention relates to an ophthalmic surgical apparatus, a control method thereof, and a surgical method using the same, and more particularly, A first operation mode for cutting a front part of the lens, a second operation mode for cutting the nucleus part of the lens, a second operation mode for cutting the nucleus part of the lens, And a control unit for controlling the light converting unit and the delivering unit according to the operation mode and the third operation mode for cutting the cornea, Characterized in that at least one of the waveform or the irradiation pattern is controlled to have a different characteristic And a surgical method using the same and a control method thereof.

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 surgical apparatus using a laser, a control method thereof, and a surgical method using the same, and more particularly, to an ophthalmic surgical apparatus capable of performing an anterior segment operation using a femtosecond laser, And a surgical method using the same.

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, conventional cataract surgery has the disadvantage that the risk of accident is high and the surgical result depends on the ability of the operator because incision of the cornea and anterior chamber of the lens and grinding of the lens nucleus proceeds manually by the operator.

In recent years, in order to solve such a problem, surgical methods of incising a lens using a laser have been proposed. However, since it is an early stage of research and development, there are limitations to apply the laser in consideration of the characteristics of each stage of cataract surgery.

Korean Patent Laid-Open Publication No. 1990-0015698

SUMMARY OF THE INVENTION The present invention has been made to solve the above-mentioned problems, and it is an object of the present invention to provide an ophthalmic surgical apparatus, a control method thereof, and a surgical method using the same, in which optimized surgery can be performed by controlling laser characteristics used in cataract surgery.

According to another aspect of the present invention, there is provided an optical communication system including a light source that generates a laser, a light conversion unit that converts parameters of the laser generated in the light source, a light transmission unit that forms a propagation path of the laser generated in the light source, And a third operating mode for cutting the cornea, and a second operating mode for cutting the cornea of the lens, and a third operating mode for cutting the cornea, Wherein at least one of the output of the laser, the pulse waveform or the irradiation pattern irradiated through the light irradiating unit according to each operation mode has different characteristics And a control unit for controlling the operation of the ophthalmic surgery apparatus.

The first laser irradiated in the first operation mode, the second laser irradiated in the second operation mode, and the third laser irradiated in the third operation mode have energy radiated per unit area at each irradiation position And the second laser among them can be controlled to transmit the greatest energy per unit area at the irradiation position.

Further, the control unit may control the irradiation of the first laser to be irradiated in the first operation mode, the second laser to be irradiated in the second operation mode, and the third laser to be irradiated in the third operation mode, As shown in FIG.

According to another aspect of the present invention, there is provided a control method of an ophthalmic surgical apparatus configured to control a light source for generating a laser and a characteristic of the laser to be irradiated, A second actuation step of irradiating a second laser capable of incising the nucleus region of the lens, and a third actuation step of irradiating a third laser capable of incising the cornea, The laser, the second laser, and the third laser are controlled so that at least one of the output, the pulse waveform, and the irradiation pattern has different characteristics from each other. have.

Among the first laser, the second laser and the third laser, the second laser can be controlled so as to transmit the greatest energy per unit area to the irradiation position.

Alternatively, the first laser, the second laser, and the third laser may be controlled so that the patterns irradiated to the respective irradiation positions are different from each other.

Further, the object of the present invention is also achieved by a method of radiating a laser beam to a lens, comprising the steps of irradiating a front laser beam onto a front lens of a lens to incise the front lens, Wherein the first laser, the second laser, and the third laser are characterized in that at least one of the output, the pulse waveform, and the irradiation pattern has a different characteristic from each other And a method of operating the anterior segment using a laser.

The first laser, the second laser, and the third laser are different in energy to be irradiated per unit area at each irradiation position, and in particular, among them, the second laser is irradiated Lt; / RTI >

Alternatively, the first laser, the second laser, and the third laser may be configured such that the patterns irradiated to the respective irradiation positions are different from each other.

According to the present invention, it is possible to perform optimized surgery while improving the safety of the surgery by using the laser parameters and irradiation patterns according to the surgical site and the operation contents.

FIG. 1 is a block diagram schematically showing the configuration of an ophthalmic surgery apparatus according to an 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 graph showing output characteristics of the laser in each step of FIG. 2,
FIG. 5 is a diagram showing irradiation patterns of the laser beams in each step of FIG. 2;

Hereinafter, an ophthalmic surgical apparatus using a laser, a control method thereof, and an anterior segment 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 illustrating the configuration of an ophthalmic surgery apparatus according to an embodiment of the present invention. As shown in Fig. 1, the ophthalmic surgical apparatus comprises a light source 110 for generating a therapeutic laser and a laser system 100 for processing and delivering a therapeutic laser. Here, the laser system 100 may include a light converting unit 120 and a light transmitting unit 130.

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 transmitting portion 130 is also configured to include 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 transmitting unit 130 is configured to be able to vary the optical path so as to vary the irradiating position of the laser irradiated through the light irradiating unit. Therefore, by driving the optical element constituting the light transmitting portion 130, the laser can be irradiated to various positions of the front anterior portion.

Specifically, the light transmitting unit 130 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. Accordingly, as the laser passes through the light transmitting portion 130, 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 transmission unit 130 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 ophthalmologic surgical apparatus according to the present embodiment further includes an image detection unit 200 for obtaining an image of the anterior segment in which surgery is performed. Here, the image detecting unit 200 may include a camera unit 210 and an optical coherence tomography (OCT) unit 220.

The camera unit 210 is a device capable of acquiring a two-dimensional image of the eye surface. The camera unit 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 transmitting unit 130 described above, and is irradiated through a light irradiating unit along a route through which the therapeutic laser is irradiated. do. 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 phenomenon and is widely used as a noninvasive diagnostic method because of its high resolution compared to computed tomography (CT). In recent years, a technique has been developed for acquiring three-dimensional images by processing a plurality of tomographic images at a very high speed. In this embodiment, OCT capable of acquiring three-dimensional images is applied to obtain tomographic images of the anterior segment, It is possible to acquire a three-dimensional image.

Thus, the surface image and the tomographic image of the eye obtained at the image detecting unit 200 can be processed by the processor and provided to the interface 500. The detailed description of the camera unit 210 and the OCT unit 220 of the image detection unit 200 is widely used in the similar technical field, and thus a detailed description thereof will be omitted.

On the other hand, the interface 500 may display an image obtained by the image detecting unit 200, including a display. 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 the patient's eye fixed on the eye interface transmitted from the camera, and can be used to select a site where the cornea is incised or to display an incision site . Further, the tomographic image of the anterior segment transmitted from the OCT unit can be used to select and display the incision area and incision pattern of the lens. Furthermore, the three-dimensional image obtained by processing the tomographic image obtained from the OCT can be used to determine the time axis of the lens and to provide a real-time image of the surgical procedure. In this way, the interface 500 can be utilized in various ways to obtain information about a surgical site, design a surgery, and display a surgical procedure by using the information obtained from the image detection unit.

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 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, As shown in FIG.

In addition, the processor 300 may perform various calculations using image data and coordinate data. For example, the processor 300 can calculate and match the coordinates of the eye surface image obtained from the camera unit 210, the tomographic image acquired from the OCT unit 220, and the three-dimensional images obtained from the tomographic image have. 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 calculate the coordinate of the coordinate, provide the image of the coordinate, or calculate the coordinates of the laser.

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 controls the operation of the surgical instrument according to various modes including the light source 110, the light converting unit 120 and the light transmitting unit 130 according to a mode input by the user through the interface 500, Controls the operation of the component.

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, various components of the light transmitting part 130 are controlled according to a user-specified operation mode or a predetermined operation mode so that the laser can be irradiated onto the set treatment area, and the locus and the pattern irradiated with the laser can be adjusted have. Further, when an abnormality occurs during operation of the surgical apparatus, a shutter (not shown) provided in the light transmitting unit may be operated to block the irradiation of the laser with the eye.

In addition, the control unit 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 segment by using a laser. In this case, by using various images obtained from the image detecting unit, It is possible to design and proceed with surgery.

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, after the patient's eyes are suctioned using the eye interface 600 while the patient is lying on the bed, the end of the light irradiation part of the surgical apparatus is lowered to dock the eye interface 600 to the end of the light irradiation part .

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.

The step of fixing the eye of the patient as described above may be performed by continuously docking the image obtained through the image detecting unit 200 so that the center of the light path irradiated with the therapeutic laser is aligned with the time axis of the eye, You can proceed.

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 proceed using 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 surgical region is set by the user's selection, the processor 300 calculates the coordinates of the corresponding region and provides the coordinates of the laser irradiation position to the control unit 400. Accordingly, the control unit 400 can control the driving of the laser system so as to irradiate the laser at the coordinates.

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. Thus, 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 incision of the cornea are completed through the laser irradiation, the ophthalmic surgical apparatus releases the docking state (S600) and removes the eye interface from the patient's eye.

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 apparatus advances the operation of cutting the anterior capsule, pulverizing the lens, and incising the cornea in such a manner that the laser is irradiated. Therefore, It is possible.

However, cataract surgery differs in the target tissues in which the procedure is performed at each stage of surgery, and the purpose of the procedure is different. Therefore, if the laser beam of the same size is irradiated in the same manner through all the steps, there is a limit to proceed with the operation reflecting the characteristics of the tissue and characteristics of each surgical stage.

Therefore, in this embodiment, it is possible to carry out a precise operation using a laser optimized for each step by irradiating with a laser having different characteristics according to each surgical stage. Here, the fact that the laser has different characteristics may mean that at least one of the output of the laser, the waveform of the pulse, the irradiation time, the diameter, and the irradiation pattern is different. Hereinafter, the characteristics of the laser according to the present embodiment will be described in detail with reference to FIGS. 4 and 5. FIG.

FIG. 4 is a graph showing the output characteristics of the laser of each step of FIG. 2, and FIG. 5 is a diagram showing irradiation patterns of the laser of each step of FIG.

As described above, the ophthalmic surgery apparatus includes a first operating mode, a second operating mode, and a third operating mode corresponding to the anterior capsule lens opening step S30, the lens necrosis step S40, and the corneal incision step S50, . Here, for convenience of explanation, the laser irradiated in the first operation mode is the first laser, the laser irradiated in the second operation mode is the second laser, and the laser irradiated in the third operation mode is the third laser. Here, each of the steps performed using the laser has different characteristics in stages.

First, because the laser is irradiated to the anterior capsule having a relatively soft tissue among the lens, a circular anterior capsular incision can be performed by a relatively small energy. In addition, a circular opening formed by anterior capsulotomy creates a path through which the light passes even after insertion of the intraocular lens, requiring precise incision.

Similarly, since the cornea is irradiated with a relatively soft tissue, the corneal incision can be performed with a small energy. In addition, the cornea forms a path through which light is incident, so that a precise incision is required.

In contrast, since the nucleus of the lens is hardened by cataract, high energy is required to dissect it. In addition, since the incision of the lens core region is easy to remove by using the suction device and the range of the laser irradiation is also wide, precise treatment as much as the circular anterior capsular incision or corneal incision is not required.

Accordingly, in this embodiment, the laser controls the light source 110, the light converting unit 120, and the light transmitting unit 130 so that the first laser, the second laser, The characteristics of the laser and the third laser can be made different from each other. Particularly, the energy that the first laser irradiates to the anterior capsule to transmit per unit area, the energy that the second laser irradiates to the lens core region, and the energy that the third laser irradiates to the cornea, In comparison, the second laser is controlled so as to transmit the largest energy per unit area at each irradiation position as compared with the first and third lasers.

At this time, depending on the surgical stage, the amount of energy transferred by the laser per unit area at each irradiation position can be controlled in various ways. For example, it is also possible to adjust the output of the laser to be irradiated through the light irradiating part, to adjust the pulse duration (duration of the on state) at the same output, To control the amount of energy transmitted.

By the control of the laser, the first laser and the third laser, which transmit relatively little energy in the first operating mode and the third operating mode, are used to precisely measure the structure It can be incised. In the second operation mode, it is possible to easily incise the lens nuclei having high hardness and to rapidly incise the relatively large area by using the second laser which transfers a relatively large energy.

As an example of such a control method, Fig. 4 shows the output characteristics of laser pulses set in this embodiment. First, when the first laser and the second laser are compared, the first laser is irradiated with a relatively small output as compared with the second laser. The pulse irradiation time t1 of the first laser is also controlled to be shorter than the pulse irradiation time t2 of the second laser. Therefore, the first laser is configured to transmit a small energy per unit area at the irradiation position as compared with the second laser. On the other hand, the third laser is also irradiated with a small output as compared with the second laser, and the irradiation time of the pulse is also made shorter. Therefore, as described above, the anterior capsular incision and the incision of the lens capsule can be precisely performed using the first laser and the third laser, which provide a relatively small energy, and the incision of the nucleus of the lens allows relatively large energy 2 laser can be used to quickly and effectively cut a hard tissue.

Here, the first laser and the second laser are controlled so that a plurality of laser pulses constituting each of the first laser and the second laser have the same output and the same irradiation time. However, as in the case of the third laser shown in FIG. 4, , t4) (a mode in which a laser pulse having a relatively high output and a short irradiation time, and a laser pulse having a low output and a long irradiation time are irradiated to each other in an intersecting manner).

However, this is an example for explaining various combinations of laser pulses constituting the laser, and the present invention is not limited to the combination of the above-described laser pulses. In addition to this, the first and second lasers may also be laser It is also possible to constitute a combination of pulses. In addition, in FIG. 4, the output of the laser and the pulse irradiation time of the laser are controlled to control the amount of energy provided per unit area. However, in addition to controlling the beam size and pulse delay time at each irradiation position of the laser, It is also possible to control the size of the substrate.

Further, the control unit 400 may control the irradiation pattern of the laser irradiated in the first operation mode, the second operation mode, and the third operation mode by adjusting the light transmitting unit 130. [ As described above, the first actuating step and the third actuating step are formed so that the interval between the pulses constituting the laser is shortened in order to proceed with a relatively precise operation, and the second actuating step is performed between the pulses Can be formed to be wide.

5 shows an example of a laser irradiation pattern for each operation mode. First, as shown in FIG. 5A, the first laser may be configured such that each laser pulse constituting the first laser partially overlaps the irradiation position of the laser pulse irradiated before. Thus, the first laser can precisely incise the anterior capsule of the lens by irradiating the laser with a very small output to be overlapped.

Then, as shown in Fig. 5B, the second laser can form a pattern in which each laser pulse is irradiated with a wide interval d1. Therefore, it is possible to rapidly perform a nuclear portion of a large area while using a laser that transmits high energy.

Further, as shown in FIG. 5C, the third laser can form a pattern in which each laser pulse is not overlapped with the first laser but is irradiated at a relatively narrow interval d2. Therefore, it is possible to precisely cut the cornea using a laser that transmits a relatively small energy.

However, the irradiation pattern of the laser shown in FIG. 5 is merely an example, and the present invention is not limited thereto, and it is needless to say that various patterns can be applied. For example, it is also possible to irradiate the third laser with the pattern shown in FIG. 5A, or to irradiate the first laser with the pattern shown in FIG. 5C. In addition, although FIG. 5 illustrates only a form in which each laser pulse is irradiated at the same interval in one irradiation pattern, a pattern for irradiating laser pulses at random intervals or at various intervals may be applied.

As described above, the present invention provides an ophthalmic surgical apparatus, a surgical method using the apparatus, and a control method thereof, in which parameters of a laser are controlled in consideration of characteristics of each surgical stage, to provide. Therefore, according to the present invention, by applying an optimal laser according to each surgical stage, it is possible to carry out precise surgery quickly and safely.

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

Claims (19)

A light source for generating a laser;
A light converter for converting a parameter of the laser generated in the light source;
A light transmission unit forming a propagation path of the laser generated in the light source;
A light irradiating part formed at an end of the light transmitting part and irradiating light to the outside; And,
A control unit for controlling the light converting unit and the transmitting unit according to a first operating mode for cutting the anterior chamber of the lens, a second operating mode for cutting the nucleus of the lens, and a third operating mode for cutting the cornea, Including,
Wherein the control unit controls the laser irradiated through the light irradiation unit to have different characteristics in at least one of an output, a pulse waveform, and an irradiation pattern according to each operation mode. The method according to claim 1,
The first laser irradiated in the first operation mode, the second laser irradiated in the second operation mode, and the third laser irradiated in the third operation mode are arranged such that the energy irradiated per unit area at each irradiation position is different Wherein the control unit controls the operation of the ophthalmic surgical apparatus. 3. The method of claim 2,
Wherein the first laser, the second laser, and the second laser are controlled so as to transmit the largest energy per unit area at the irradiation position. The method according to claim 1,
Wherein the control unit controls the first laser to be irradiated in the first operation mode, the second laser to be irradiated in the second operation mode, and the third laser to be irradiated in the third operation mode, And a control unit for controlling the operation of the ophthalmic surgical apparatus. 5. The method of claim 4,
Wherein the first laser comprises a plurality of laser pulses sequentially irradiated and each of the laser pulses has a pattern irradiated so that a part thereof overlaps an irradiation area of a laser pulse irradiated at each irradiation position Ophthalmic surgical apparatus. 5. The method of claim 4,
Characterized in that the first laser comprises a plurality of laser pulses sequentially irradiated and has a pattern in which two or more pulses with different energy transmitted per unit area at each irradiation position are repeatedly irradiated. . 5. The method of claim 4,
Characterized in that the first laser, the second laser and the third laser are irradiated so that the second laser transmits the greatest energy per unit area to the irradiation position, and the third laser is irradiated so as to transmit the smallest energy . delete delete delete delete delete delete delete delete delete delete delete delete

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