KR101902862B1 - An ophthalmic treatment apparatus and method for controlling that - Google Patents

Abstract

[0001] The present invention relates to an ophthalmic treatment apparatus and a control method thereof, which comprises a setting unit formed to set a treatment mode, a treatment light irradiation unit irradiating treatment light to the target position of the fundus a plurality of times to perform treatment, A monitoring unit for monitoring state information of the target position by the treatment light while the irradiation light is being irradiated; and a controller for determining whether the treatment intensity according to the treatment mode has been reached using the information monitored by the monitoring unit, And a control unit for controlling the operation of the treatment light irradiation unit, and a control method thereof.

Description

TECHNICAL FIELD [0001] The present invention relates to an ophthalmic treatment apparatus and a control method thereof,

The present invention relates to an ophthalmic treatment apparatus and a control method thereof, and more particularly, to an ophthalmologic treatment apparatus and a control method thereof for detecting a state of a target position during treatment and controlling treatment contents.

In recent years, techniques for treating tissue by irradiating light to change the state of tissues to transmit energy to human tissues have been widely applied. Particularly, it is widely used for laser-assisted edge.

Many devices for treating anterior segment lesions, such as corneal surgery, glaucoma or cataract surgery, have been developed, and devices for treating various lesions of the fundus region including macular degeneration have been developed . Such a surgical apparatus is also disclosed in Korean Patent Laid-Open Publication No. 10-2014-0009846.

Such a treatment device transfers energy to the target position through light to induce a state change of the tissue to proceed treatment. However, if energy is excessively transferred to the target site, damage to the target tissue as well as the adjacent tissue may occur, which may cause visual impairment particularly in the treatment of ophthalmic lesions. Therefore, it is necessary to monitor the state of therapy during treatment, but there is a limit to detecting minute changes in tissue.

Korean Patent Publication No. 10-2014-0009846

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 optical therapy apparatus and a driving method thereof that can monitor the state change of tissue inside a treatment area during treatment in real-

In order to attain the above object, the present invention provides a treatment method comprising a setting unit configured to set a treatment mode, a treatment light irradiation unit for performing treatment by irradiating treatment light to the target position of the fundus a plurality of times, A monitoring unit for monitoring the state information of the target position by the treatment light during a predetermined period of time, and a control unit for determining whether the treatment intensity according to the treatment mode has been reached using the information monitored by the monitoring unit, And a control unit for controlling the operation of the irradiation unit.

For example, if the controller determines that the information detected by the monitoring unit does not reach the set treatment intensity, the controller adjusts the parameter of the treatment light. If it is determined that the set treatment intensity has been reached, It is possible to control to terminate the irradiation of the irradiation light.

Here, the treatment light is irradiated so as to have a spot size capable of transferring energy to a plurality of RPE cells located in the target area, and the plurality of RPE cells are irradiated with a plurality of therapeutic light, Is changed. Specifically, the therapeutic light may have a spot size that transfers energy to at least 50 RPE cells. Alternatively, the treatment light may have a spot size of 50 mu m or more in diameter in the fundus.

The monitoring unit may be configured to detect an amount of RPE cells whose state changes by treatment among a plurality of RPE cells disposed at a target position to which the therapeutic light is irradiated, and to monitor the progressed treatment intensity at the target position .

Here, the monitoring unit may be configured using an optoacoustic sensor or a reflectometry sensor. Alternatively, the monitoring unit may include a second monitoring unit configured with a first monitoring unit and a reflectometry sensor, each of which is composed of an optoacoustic sensor, and the first monitoring unit and the second monitoring unit The control unit may control to stop irradiating the treatment light to the target position when it is determined that the set treatment intensity is reached by at least one of the monitored information.

On the other hand, the setting unit may be configured to display a plurality of treatment intensities having different values, the user being configured to select a treatment intensity to set a treatment mode, or configured to display a plurality of treatment lesions, Mode. ≪ / RTI >

The above object of the present invention can be achieved by a method for regenerating RPE cells, comprising the steps of selecting a treatment intensity through a setting unit, irradiating treatment light to a target position in which a plurality of RPE cells are arranged, Determining whether the set therapeutic intensity has been reached based on the monitored information, and determining whether the set therapeutic intensity has been reached based on the monitored information, And controlling the therapeutic light parameter.

In order to achieve the above object, the present invention provides a treatment light irradiation unit for irradiating a treatment light to a target position located in a fundus a plurality of times, A second monitoring unit for measuring the state information of the target position during the irradiation of the treatment light in a second mode different from the first mode and a second monitoring unit for measuring the state information of the target position during the first monitoring unit and the second monitoring And a control unit for controlling parameters of the treatment light based on the information measured by the unit or determining whether to irradiate the treatment light.

Here, the first monitoring unit measures information on the treatment progress state or the treatment end time with respect to the target position, and the second monitoring unit can measure information on whether or not an abnormality occurs during treatment.

According to the present invention, energy is transferred to a plurality of RPE cells located in a target area and the therapy is progressed, thereby effectively controlling the therapeutic intensity.

In addition, there is an advantage that optimal treatment can be performed by determining the end point of the treatment while monitoring the progress of the treatment in real time during the treatment.

In addition, since the monitoring unit is provided to measure the state information of the tissue in a different manner, the state change information can be effectively monitored during the treatment.

Furthermore, it is possible to determine whether or not an abnormality occurs during treatment and to stop the procedure in case of an abnormality, so that it is possible to effectively cope with an unexpected situation occurring during treatment.

1 is a schematic view schematically showing an ophthalmic treatment apparatus according to a first embodiment of the present invention;
FIG. 2 is a sectional view of the area A of FIG. 1,
3 is a block diagram schematically showing the configuration of the second monitoring unit,
4 is a view showing a state in which curing light is irradiated on the fundus,
5 is a graph showing the irradiation pattern of the treatment light and thus the measurement signal of the monitoring part,
FIG. 6 is a view showing an example of display through a display of the setting unit,
7 is a view showing another example displayed through the display of the setting unit,
8 is a flowchart showing a control method of the ophthalmic treatment apparatus of Fig. 1,
9 is a flowchart showing a control method of an ophthalmic treatment apparatus according to a second embodiment of the present invention,
FIG. 10 is a graph showing an irradiation pattern of treatment light according to the control method of FIG. 9,
11 is a graph showing another example of adjusting the therapeutic light parameter,
12 is a cross-sectional view showing a state in which the anterior segment surface is treated using the present invention.

Hereinafter, an ophthalmic treatment apparatus 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. However, the present invention is not limited thereto, and various devices may be added, modified or omitted.

The ophthalmic treatment apparatus described below will be described as an apparatus for treating fundus lesions, but the present invention can also be applied to a treatment apparatus for treating other lesions other than fundus lesions. For example, the present invention may be applied to a therapeutic apparatus for treating an anterior segment lesion such as glaucoma treatment, and may be applied to a therapeutic apparatus for treating lesions of skin tissue. As described above, it should be noted that the present invention is not limited to the ophthalmic treatment apparatus described below, and it can be widely applied to a treatment apparatus for optically treating other lesions.

1 is a schematic view schematically showing an ophthalmic treatment apparatus according to a first embodiment of the present invention. 1, an ophthalmic treatment device 1 according to the present invention includes a treatment light generating part 10 for generating a treatment beam, a collimating light generating part for generating a aiming beam 20, and a beam delivery unit 30 for forming a traveling path of the therapeutic light and the collimated light. In addition, a monitoring unit 40 for detecting tissue state information of a target position irradiated with treatment light, and a control unit 60 for controlling various components based on information sensed by the monitoring unit.

The curing light generating unit 10 may include various optical devices for processing characteristics of light generated from the therapeutic light source and the therapeutic light source. The therapeutic light may be composed of a laser, and the therapeutic light source may include a laser medium such as Nd: YAG, Ho: YAG or the like or a laser diode capable of oscillating the laser. The therapeutic light source is configured to irradiate a laser having an appropriate wavelength, pulse width, and power, with the lesion or energy taking into account the characteristics of the tissue at the target location. And various devices such as various electric circuits for generating a laser, an optical filter, and a shutter.

The collimator light generating unit 20 generates an aiming beam to be irradiated to the treatment area. The aiming light is a configuration for displaying the position so that the operator can confirm the position where the treatment light is irradiated before the treatment light is irradiated or while the treatment light is irradiated. For example, the collimated light has a wavelength in the visible range, and the operator can confirm the treatment area by the collimated light reflected from the treatment area.

The collimating light generating unit 20 irradiates collimated light in a single spot shape and irradiates the collimated light to the target position through the same path as the irradiation path of the treatment light. Alternatively, it is possible to irradiate a pattern in the form of a plurality of spots so that a plurality of positions where the therapeutic light is irradiated can be displayed. In addition to this, the collimated light can be illuminated in the form of a lattice or a boundary line to display a region irradiated with the therapeutic light.

However, if it is possible for a surgeon to confirm a treatment area through a separate interface such as a monitor, the collimator light generator may be omitted.

On the other hand, the beam delivery section 30 is constituted by a plurality of optical elements and constitutes an optical path through which the treatment light travels. The aim beam and the probe beam of the second monitoring unit to be described later can also proceed along the beam delivery portion. Here, the optical path of the collimated light and / or the detected light is configured to share at least a part of the optical path of the therapeutic light, but it is also possible to form a separate optical path if necessary.

Specifically, the beam delivery unit 30 includes a plurality of beam combiners 31. [ As a result, the treatment light, the collimated light, and the detection light can be irradiated to the treatment area through the beam delivery part 30, respectively, as shown in FIG. Then, the collimated light and the detected light reflected from the treatment area may advance in the direction in which the operator's eyes are positioned through the beam delivery unit 30, or may enter the second monitoring unit 42 again.

The beam delivery portion 30 includes a scanner 32 that changes the position where the light is irradiated. The scanner 32 includes at least one reflecting mirror and a driving unit for rotating the reflecting mirror. The rotating position of the reflecting mirror for reflecting light may be changed to change the irradiation position of the light.

In addition, although not specifically shown in the drawings, the beam delivery portion may further include a plurality of optical lenses for focusing or dispersing light, and optical elements such as optical filters.

An object part 70 is provided at the end of the beam delivery part 30. [ The alternative unit 70 includes a contact lens in contact with the patient's eye in a configuration in which the eye of the patient to be treated is located. Further, a suction device for sucking and fixing the patient's eyes so that the patient's eyes can be fixed during the procedure may be included.

The treatment light irradiation unit includes the treatment light generating unit 10 and the beam delivery unit 30. The treatment light generated by the treatment light generating unit 10 is transmitted to the beam delivery unit 30 and the solution unit 70 ) Are examined as the treatment area of the fundus. The collimating light irradiating unit includes a collimating light generating unit 20 and a beam delivering unit 30. The collimating light generated by the collimating light generating unit is also transmitted through the beam delivery unit 30 and the alternative unit 70 The area of treatment of the fundus is investigated.

2 is a sectional view of the area A of FIG. 2 (A) is a diagram showing a retinal tissue of a patient corresponding to a treatment region. These retinal tissues are generally composed of an internal limiting layer, a nerve fiber layer, a ganglion cell layer, an inner plexiform layer, an inner nuclear layer, It consists of ten layers: the outer plexiform layer, the outer nuclear layer, the outer limiting layer, the photoreceptor layer, and the RPE layer (retinal pigment epithelial layer) Inner depth direction).

Among these, the RPE cell layer forms a boundary layer in the backward direction among the above ten layers, and is formed as a tight junction structure. Bruch's membrane is located below the RPE layer. These RPE layers supply nutrients and oxygen from blood vessels located in the choroid to supply nutrients to photo receptors and discharge the waste generated from photoreceptors through the bruch membrane.

If some of the RPE cells forming the RPE layer fail to perform their normal functions, the photoreceptors located in front of the RPE cells will become necrotic due to inadequate nutrient supply or oxygen supply. In order to solve this problem, the ophthalmic treatment apparatus according to this embodiment irradiates the RPE cell layer with therapeutic light to transfer energy, and induces the regeneration of new RPE cells, thereby proceeding the treatment.

More specifically, the treatment light generated in the treatment light generating portion 10 has a wavelength in a visible light or near infrared region. The light of this wavelength is transmitted to the cell layer (the first to ninth cell layers) located in front of the retina with little absorption, and then absorbed into melanomas existing in the RPE cell of the RPE cell layer. Thus, as the amount of energy absorbed in the melanocytes increases, the RPE cells undergo a state change with increasing temperature, and the RPE cells in which the state is changed are replaced with healthy RPE cells. It is believed that microbubbles are formed on the surface of the melanomas as the temperature rises, and RPE cells are selectively necrosed as microbubbles grow gradually.

In the course of such treatment, excessive amounts of energy delivered by the therapeutic light can damage adjacent photoreceptors as well as RPE cells at the target location, and can severely impair visual acuity. Therefore, the ophthalmologic treatment apparatus of FIG. 1 includes a monitoring unit 40, and monitors the state of the tissue during treatment through the monitoring unit to check the treatment progress in real time.

The monitoring unit 40 of the present embodiment may be configured to include a plurality of monitoring units 41 and 42 that independently perform monitoring operations. Specifically, the monitoring unit 40 may include a first monitoring unit 41 and a second monitoring unit 42. [ The first monitoring unit 41 may measure the status information of the target position in a first manner and the second monitoring unit 42 may measure the status information of the target position in the second manner. That is, the first monitoring unit 41 and the second monitoring unit 42 can monitor the status information of the target position in different ways, thereby making it possible to compensate for the shortcomings of each measurement method.

For example, the first monitoring unit 41 may be configured using an optoacoustic sensor. A photoacoustic sensor is a device for measuring an acoustic signal generated by light absorption. As described above, during the course of treatment, the RPE cells at the target position absorb the therapeutic light and the state changes, and an acoustic signal is generated in this process. These acoustic signals are considered to be generated during microbubbles generation as the temperature of RPE cells increases. The first monitoring unit 41 measures this and measures the state change of the target position and the progress of the treatment.

The first monitoring unit 41 of this embodiment is installed in the contact lens of the alternative unit 70 and can measure an acoustic signal transmitted from the patient's eye in contact with the patient's eye. However, this is merely an example, and the first monitoring unit may be constituted by a separate device from the contact lens, and may be installed so as to be in contact with the eye or the area adjacent to the eye of the patient.

Meanwhile, the second monitoring unit 42 may be composed of a reflectometry sensor. The second monitoring unit 42 can receive the reflected light reflected from the target position and analyze it to determine the status information of the target position included in the reflected light. Thus, it is possible to measure whether or not the state of the target position has changed and the progress of the treatment.

The second monitoring unit 42 of the present embodiment receives light reflected by the therapeutic light irradiated to the target position. As shown in FIG. 2, a part of the treatment light irradiated to the target position is absorbed in the target position, and a part thereof is reflected and received by the sensor of the second monitoring unit 42 through the beam converter 31. The second monitoring unit 42 analyzes the parameters of the received reflected light and monitors the status information of the target position. For example, as micro-bubbles are generated in the RPE cells by the therapeutic light, the frequency-dependent components of the signal in the 5 to 50 MHz band are increased by the reflected light, and the second monitoring unit 42 calculates the state of the target position And the progress of the treatment. However, various parameters other than the frequency components included in the reflected light can be used.

As in the present embodiment, since the second monitoring unit 42 performs monitoring using the reflected treatment light, there is an advantage that the change of the target position due to each treatment light can be monitored in real time. However, this is merely an example, and it is also possible to irradiate a separate detection light for monitoring to the target position, and to receive the detection light reflected from the target position to monitor the light, instead of receiving the treatment light.

As described above, the first monitoring unit of the present embodiment is constituted by a photoacoustic sensor, and the second monitoring unit is constituted by using a reflectometer sensor. However, it is also possible to configure the first monitoring unit or the second monitoring unit by using various sensors. As another example, it is also possible to configure the second monitoring unit as an interferometry sensor instead of a reflectometry sensor as in Fig.

3 is a block diagram schematically showing the configuration of a second monitoring unit according to another example. When the second monitoring unit is constituted by an interferometer sensor such as an OCT apparatus, the second monitoring unit can use the interference information of the reflected light reflected from the target position. Thus, it is possible to acquire various tomographic information including temperature information of the target position, state change, and treatment progress state. 3, while the conventional OCT device acquires a tomographic image of a predetermined region while moving the irradiation position in the horizontal direction (reference to the retina plane of the fundus), the second monitoring unit 142 of Fig. During the proceeding, tomographic information of the target position is obtained a plurality of times or continuously. As the light path changes according to the state change of the tissue at the target position, the interference information detected by the second monitoring unit 142 changes, and the state change of the target position can be detected using the interference information.

 3, the second monitoring unit 142 constituted by the interferometer sensor includes a detection light source 143, a beam splitter 144, a reference light reflector 145, and a detection unit 146 ).

The detection light source 143 may be a light source generating a low coherent beam in the case of the SD OCT and a swept source light source capable of changing the wavelength of the light in the case of the SS OCT.

The light emitted from the detection light source 143 passes through the optical splitter 144 and is divided into two lights of the detection light and the reference light. The reference light travels along the first path P1 to reach the reference light reflector 145, and then is reflected by the reference light reflector 145. The detection light travels along the second path P2 and is irradiated through the beam delivery portion 30 to the target position, and then is reflected at the target position. The reflected detection light and the reference light are recombined in the optical splitter 144 and proceed to the detection unit 146.

Here, interference occurs between the reference light and the detection light that is coupled through the optical splitter 144. The detection unit 146 detects the state information of the target position using the detection light and the interference light based on the reference light. The detector 146 may be configured using an array detector in the case of the SD OCT and a photo diode in the case of the SS OCT.

The second monitoring unit 142 of FIG. 3 uses the interference information of the detected light by the interferometer to measure the temperature of the target position, the thickness of the tissue, the refractive index, the movement of the tissue, It is possible to grasp a minute state change of the state. In FIG. 3, the second monitoring unit is replaced with the interferometer sensor. However, it is also possible to replace the first monitoring sensor with the interferometer sensor, and configure the monitoring unit using the interferometer sensor and the reflection sensor.

As described above, the first monitoring unit 41 and the second monitoring unit 42 respectively measure the state change of the target position in a different manner, and transmit this information to the control unit 60. The control unit 60 can control the operation of the treatment apparatus based on the information measured by the first monitoring unit 41 and the second monitoring unit 42. [

The control unit 60 controls the operation of various components including the treatment light generating unit 10, the collimating light generating unit 20, and the beam delivery unit 30. Thus, the treatment position, the treatment time, the parameters of the treatment light, and the like can be variously controlled. In performing such control, the control unit 60 controls various components in consideration of the information monitored by the monitoring unit 40 described above.

Specifically, the control unit 60 controls the treatment light to be irradiated to the same target position a plurality of times during the treatment for one target position. In this process, if it is detected that the treatment intensity is not progressed to the treatment intensity set through the monitoring unit 40, the control unit controls the treatment light irradiation unit to adjust the treatment light parameter. At this time, the parameter of the treatment light is adjusted so as to increase the energy delivered per unit area of the target position. For example, the control unit 60 may control to sequentially increase the output of the treatment light until the treatment is finished. On the other hand, if it is detected through the monitoring unit that the target position is set to the treatment intensity, the control unit 60 may terminate the treatment of the target position by terminating irradiation of the target position. The control contents of the control unit will be described in more detail below.

Here, the control unit 60 may utilize the information measured by the first monitoring unit 41 and the second monitoring unit 42 in various ways. For example, when all the information measured in the first monitoring unit and the second monitoring unit satisfies the first condition, it is determined that the state of the target position has reached the first condition and the corresponding control can be performed have. Alternatively, the status information of the target position may be determined based on information measured in either the first monitoring unit or the second monitoring unit, and when the information to be the reference is determined to be unreliable due to an unexpected event, And the state information may be determined using the information measured in the remaining one.

However, if it is detected that the treatment of the target position has been completed through any one of the two monitoring units 41 and 42, the control unit 60 of the present embodiment determines that the treatment of the target position is terminated, The irradiation of light is terminated. As described above, it is common that RPE cells generate fine bubbles while the state changes, generate a sound signal, change the light path due to cell expansion or damage, or generate scattered light. Exceptionally, however, changes in state may result in weaker sonic signal strengths, or slight optical changes (eg, substantially no change to the optical path, or the size of the reflected scattered light). Even in such an exceptional case, the present embodiment can detect the state change in a different manner from each other and determine the end point of the treatment, thereby preventing excess energy from being transmitted to the target position, thereby damaging the tissue.

On the other hand, FIG. 4 is a view showing a state in which the treatment light is irradiated on the fundus. As shown in Fig. 4, the size of the spot of the therapeutic light irradiated to the target position can be formed such that a plurality of RPE cells C are positioned within the boundary S of the spot based on the RPE cell layer. Accordingly, during the treatment of one target site, energy is transferred to a plurality of RPE cells located at the target position, and the treatment progresses. The monitoring unit 40 detects a change in state of the plurality of RPE cells The progress of treatment progress can be monitored.

The RPE cells exposed to the therapeutic light maintain their original RPE cells when sufficient energy is not delivered, or when they are transferred with sufficient energy, they are regenerated into new RPE cells. Thus, since one RPE cell follows one of two processes when irradiating therapeutic light, it is difficult to control the therapeutic intensity when the spot size of the therapeutic light is focused on only one RPE cell. In contrast, when the therapeutic light is configured to transmit energy to a plurality of RPE cells as in the present embodiment, the therapeutic intensity can be controlled by controlling the amount of RPE cells in which the state changes by treatment among a plurality of RPE cells . Therefore, according to the present embodiment, it is possible to proceed with the optimal treatment intensity according to the lesion, the treatment position, and the condition of the patient. Of course, even if the spot size of the therapeutic light transfers energy to only one RPE cell, it is possible to adjust the therapeutic intensity in such a manner as to adjust the interval of the target positions irradiated with the therapeutic light. However, in this case, the treatment time is increased. In addition, since the size of the RPE cells varies depending on the location of the retina (for example, the diameter of the RPE cells in the center of the fundus is 10 to 15 μm and the diameter of the RPE cells in the periphery of the fundus is 50 μm or more) It is necessary to adjust the interval between the target positions according to the position of the treatment area.

As described above, when the spot size of the therapeutic light is small, the treatment time is increased and the treatment intensity can not be adjusted in various ways. On the other hand, when the spot size of the therapeutic light is excessively large, it is difficult to treat local lesions and it is difficult to treat a target site adjacent to a blood vessel or macula. Therefore, the spot size S of the therapeutic light can be configured such that 10 to 1000 RPE cells (C) are located inside the boundaries of the spots on the basis of the region irradiated to the RPE cells, preferably 50 to 500 RPE < / RTI > cells (C) are located. Alternatively, the spot size S of the treatment light can be configured to have a diameter of 50 mu m to 1000 mu m.

In the present embodiment, the spot size of the treatment light can be configured to have a diameter of 100 to 400 mu m. Furthermore, it is possible to configure the spot size to be adjusted according to the position of the treatment area. For example, if the treatment area is located inside the fundus, the diameter of the spot is controlled to 150 to 200 mu m, and if the treatment area is located at the periphery of the fundus, the diameter of the spot can be controlled to 250 to 350 mu m.

As such, while the therapeutic light is irradiated with the therapeutic light to a plurality of RPE cells located at the target position, the monitoring unit 40 monitors the treatment progress of the target position in real time. Here, the monitoring unit 40 monitors the progress of the treatment by detecting the amount or ratio of the RPE cells in which a state change has occurred among a plurality of RPE cells in the corresponding region, and the control unit 60 calculates the treatment intensity Can be determined.

5 is a graph showing an irradiation pattern of treatment light and thus a measurement signal of a monitoring part. As shown in FIG. 5A, the treatment light irradiation unit irradiates the treatment light to the target position a plurality of times, and each treatment light is irradiated so that the output sequentially increases. Meanwhile, the signal measured at the monitoring unit may be as shown in FIG. 5B (for convenience of illustration, the signal measured at the first monitoring unit of the monitoring unit).

As shown in Fig. 5, while the treatment light is irradiated four times (T1 to T4), a measurement value below the effective value is detected in the monitoring unit 40. [ The measured value detected in this section is the noise value detected in the normal state. Accordingly, the controller 60 determines that the state change of the RPE cells does not occur while the measured value below the effective value is sensed.

At the time when the fifth treatment light T5 is irradiated, the monitoring unit 40 detects a measured value equal to or greater than the effective value, and the controller 60 determines that some RPE cells of the target position have started to change state . When the sixth treatment light T6 and the seventh treatment light T7 are irradiated, the value measured by the monitoring unit 40 also gradually increases, and the control unit 60 gradually changes the state of the RPE cells Of the total.

As described above, as the output of the therapeutic light is increased, the amount or the proportion of the RPE cells whose state changes is increased, thereby increasing the value measured by the monitoring unit 40. Here, the treatment intensity can be judged by the amount or ratio of RPE cells in which the state changes among a plurality of RPE cells located at the target position. The control unit 60 can refer to the data stored in the memory and determine the treatment intensity by matching the measured value with the pre-stored data. As described above, the controller 60 can determine the treatment progress progressing to the target position in real time while the treatment light is irradiated. When the value measured by the monitoring unit 40 exceeds a value corresponding to the predetermined treatment intensity (measured value at T7 in FIG. 5), it is determined that the treatment has been performed at the target setting intensity at the position, The treatment for the position is terminated.

On the other hand, as shown in FIG. 1, the ophthalmologic treatment apparatus 1 may further include a setting unit 80 in which a user selects a treatment mode. The setting unit 80 includes a display and operation buttons that can be operated by the user. The selected treatment mode includes information on the intensity of the treatment, and information on various parameters such as the irradiation pattern of the treatment light may be included. Accordingly, when the user selects the treatment mode through the setting unit 80, the control unit 60 controls each component so as to proceed the corresponding treatment.

FIG. 6 shows an example of display through the display of the setting unit. The setting unit 80 of FIG. 6 is configured to select the treatment intensity for each target position, as a treatment mode. In one example, the therapeutic intensity may be expressed as the ratio of RPE cells in which the state changes by treatment among a plurality of RPE cells located at the target position.

In FIG. 6, ASV 20 (auto-set value 20) indicates the therapeutic intensity at which about 20% of the RPE cells in the corresponding position change state, and ASV 50 indicates the therapeutic intensity . When the treatment intensity is set as described above, the control unit 60 irradiates the treatment light through the monitoring unit 40 until the treatment intensity reaches the treatment intensity set at each target position.

Fig. 7 shows another example displayed through the display of the setting section. The setting unit 80 of FIG. 7 displays the name of the lesion to be treated as a treatment mode. For example, typical eye lesions such as central serous chorioretinopathy (CSC), diabetic macular edema (DME), and dry AMD (dry age-related macular degeneration) Can be displayed. Therefore, the user can select the treatment mode according to the lesion of the patient to be treated.

The treatment mode of FIG. 7 may also include information on each different treatment intensity. For example, the results of clinical trials show that CSCs can be treated with low therapeutic intensity, and RPE cells are relatively healthy, and DME has to be treated with high therapeutic intensity due to poor RPE cell status. And dry AMD showed higher treatment intensity than CSC and lower treatment intensity than DME. Therefore, when the user selects the treatment mode using the treatment lesion, the treatment is set to proceed according to the treatment intensity suitable for the lesion.

For example, when the CSC mode is selected, the treatment intensity may be set in a range of ASV 20 to 40, and the treatment intensity may be set in a range of ASV 40 to 60 when the dry AMD mode is selected, The therapeutic intensity may be set in the range of ASV 60 to 80. [ Further, as shown in FIG. 7, the levels of treatment intensity for each lesion are classified as high, medium and low, and the treatment intensity is further increased within the treatment intensity range according to each lesion And can be set to be subdivided.

As described above, the ophthalmologic treatment apparatus 1 of the present embodiment can be configured such that the spot size of the treatment light is irradiated to a plurality of RPE cells, and treatment can be performed at various treatment intensities according to the user's selection. In addition, the monitoring unit 40 can monitor the status information of the target position in a different manner using a plurality of monitoring units 41 and 42, thereby enabling safe and optimized treatment.

FIG. 8 is a flowchart showing a control method of the ophthalmic treatment apparatus of FIG. 1. FIG. Hereinafter, the control method of the above-described ophthalmologic treatment device 1 will be described in detail with reference to Fig.

When the treatment area is determined according to the lesion of the patient, the anterior segment of the patient is fixed to the alternative unit 70 and the treatment is continued. The treatment proceeds in such a manner that the treatment light is irradiated to a plurality of target positions distributed in the treatment area to proceed the treatment. Here, the treatment is performed by irradiating a plurality of treatment lights to one target position, and when the treatment of the target position is completed, the treatment light irradiation position is changed to the next target position and the treatment is performed. However, in FIG. 8, the process of initially treating the target position will be described for convenience of explanation.

In order to proceed with the treatment, the user selects the treatment mode through the setting unit 80 (S10), and information on the selected treatment mode is transmitted to the control unit 60. [ The control unit 60 drives the treatment light irradiation unit to irradiate the treatment light based on the selected treatment mode (S20).

When the treatment light is irradiated, the monitoring unit 40 performs monitoring of the status information of the target position. At this time, the first monitoring unit 41 and the second monitoring unit 42 independently monitor the status information of the target position.

During the above step, the controller 60 determines whether the treatment has progressed to the set treatment intensity based on the information monitored by the first monitoring unit 41 (S30). In addition, based on the information monitored by the second monitoring unit 42, it is determined whether the treatment has progressed to the set treatment intensity (S40). In FIG. 8, it is shown that the determination step (S30) using the first monitoring unit and the determination step (S40) using the second monitoring unit are sequentially performed, but the present invention is not limited to this order. The two steps S30 and S40 may be simultaneously performed at a cycle corresponding to the irradiation period of the treatment light, and may be continuously performed during the treatment.

If it is determined that the set treatment intensity has not been reached in both the determination step S30 using the first monitoring unit and the determination step S40 using the second monitoring unit, the controller 60 determines that the treatment of the target position has not been completed And adjusts the parameter of the treatment light (S50). Here, the treatment light parameters are adjusted so that the energy delivered per unit area of the target position sequentially increases by the treatment light, and the magnitude of the output of the treatment light among the parameters can be increased, for example. Thereafter, the control unit 60 irradiates the treatment light having the adjusted parameter to the target position, and repeats the above-described steps.

However, if it is determined that the treatment intensity reaches the set treatment intensity in any of the determination step S30 using the first monitoring unit and the determination step S40 using the second monitoring unit, It is judged that it is completed. Therefore, the irradiation of the therapeutic light to the target position is terminated (S60), the irradiation position of the therapeutic light is changed to the other target position, and the above-described steps S20 to S70 are repeated to perform the treatment.

Hereinafter, an ophthalmic treatment apparatus and a control method thereof according to a second embodiment of the present invention will be described with reference to Figs. 9 and 10. Fig. In describing the present embodiment, however, the same or similar components and steps as those of the above-described first embodiment are replaced with the drawings and the description of the first embodiment in order to avoid duplication of description.

The monitoring unit of the above-described first embodiment utilizes both the first monitoring unit and the second monitoring unit for the purpose of monitoring progress of the treatment progress. On the other hand, in the present embodiment, the information measured in each monitoring unit can be utilized for control of different purposes, taking into account the characteristics of the measurement methods of the first monitoring unit 41 and the second monitoring unit 42.

As described above, the first monitoring unit 41 receives the sound wave signal generated from the target position, converts it into an electrical signal, and transmits the electrical signal to the control unit 60. Since a complicated operation is not required, There is a relatively fast advantage. However, the information sensed by the first monitoring unit 41 may include a signal due to a separate event occurring at a position other than the target position, which is relatively low in accuracy.

In contrast, since the second monitoring unit 42 uses the reflected light reflected from the target position, there is an advantage that the state information of the target position can be accurately determined compared to the first monitoring unit. However, since the second monitoring unit 41 undergoes various calculation processes in order to detect a change in the parameter of the reflected light, there is a disadvantage that the operation speed is slower than that of the first monitoring unit (in particular, In the case of an interferometer sensor, the interference signal is analyzed through a complicated calculation process such as Fourier transform, so that the processing speed is relatively delayed.

Therefore, in the ophthalmologic treatment apparatus of the present embodiment, in consideration of the fast calculation speed of the first monitoring unit 41, the information detected by the first monitoring unit 41 is used as a treatment progress state or a treatment end point . ≪ / RTI > In consideration of the accuracy of the second monitoring unit 42, information sensed by the second monitoring unit 42 may be used to determine whether an odd event has occurred during the treatment.

The control unit 60 determines whether the treatment progresses (for example, whether minute bubbles have begun to occur among the RPE cells at the target position, the number of the RPE cells at the target position, The percentage of RPE cells in which microbubbles are generated, etc.) and the end of treatment. The end of treatment may be determined based on whether a value measured by the first monitoring unit (hereinafter referred to as a first measured value) has reached a predetermined first reference value (a value corresponding to the set treatment intensity). If it is determined that the treatment is completed, the control unit may stop irradiation of the treatment light to the target position, and may change the irradiation position of the treatment light to another target position to proceed the treatment. As such, the first monitoring unit can grasp the state change of the target position due to each treatment light in real time through quick calculation, and utilize it for the control.

Meanwhile, as described above, the second monitoring unit 42 can continuously monitor whether abnormality occurs in the target position during the treatment. Here, an anomaly can include various events. For example, when the therapeutic light modifies the RPE cells in a manner other than a normal mechanism, an abnormality occurs in the retinal surface tissue, and the like.

The second monitoring unit 42 is capable of acquiring highly accurate information on the target position (in particular, when configuring the second monitoring unit as an interferometer sensor, as shown in FIG. 3, Events can be identified and identified). Accordingly, when the measured value (hereinafter referred to as the second measured value) is greater than the second reference value (value corresponding to the occurrence of abnormality), the control unit 60 uses the information measured by the second monitoring unit 42 It can be judged that it has occurred.

Here, the second measured value may be variously processed values from the information obtained by the second monitoring unit. For example, the second reference value may be the value itself obtained by the second monitoring unit. Alternatively, it may be a difference value from the previously measured value while the second monitoring portion measures a plurality of times.

If it is determined that an abnormality has occurred through the information measured by the second monitoring unit 42, the control unit 60 can control to immediately stop the treatment light irradiation irrespective of the information measured by the first monitoring unit 41 have. Then, it can be displayed on the outside via a separate indicating unit 90 (see FIG. 1), thereby notifying the user of the occurrence of an abnormality.

9 is a flowchart showing a control method of an ophthalmic treatment apparatus according to a second embodiment of the present invention. Hereinafter, the control method of the ophthalmologic treatment device 1 will be described in detail with reference to Fig.

The control method of the ophthalmic treatment apparatus according to the present embodiment also selects the treatment mode (S110) as in the first embodiment, and performs the step of irradiating the treatment light to the target position (S120).

When the treatment light is irradiated, the first monitoring unit 41 and the second monitoring unit 42 monitor the state information of the target position (S130). In FIG. 9, the monitoring step S130 is shown to be performed after the treatment light step S120, but it is not limited to this order, and may be continuously performed during the treatment.

If the first measured value measured by the first monitoring unit 41 is lower than the first reference value through this step, the controller 60 determines that the treatment of the target position is not completed and adjusts the parameter of the treatment light S140). For example, the magnitude of the output of the therapeutic light in the parameter can be increased. Then, the control unit 60 controls the treatment light irradiation unit to irradiate the treatment light having the adjusted parameter to the target position (S120). And, while the first measured value is lower than the first reference value, steps S120 to S140 are repeatedly performed, whereby the treatment light is irradiated to the target position a plurality of times.

If the first measured value measured by the first monitoring unit 41 is greater than the first reference value, the controller 60 determines that the treatment of the target position is completed. Accordingly, the irradiation of the treatment light to the target position is terminated (S150), the treatment light irradiation position is changed to another target position, and the above-described steps are repeated to perform the treatment.

In the above-described process, the second monitoring unit 42 continuously monitors whether or not an abnormality has occurred. When the second measured value measured by the second monitoring unit 42 is smaller than the second reference value, .

However, if the measured value measured by the second monitoring unit 42 is greater than the second reference value, the controller 60 determines that an abnormality has occurred, stops the treatment light irradiation, and immediately stops the treatment on the target position S170). This step is performed immediately upon detection of an abnormality regardless of whether the first measured value is higher or lower than the first reference value. Then, the control unit 60 displays the occurrence of abnormality to the user through the notification unit 90 (S180).

10 is a graph showing an irradiation pattern of treatment light according to the control method of FIG. In FIG. 10 (a), minute bubbles are detected in the RPE cells at the target position when the fifth treatment light is irradiated (ASV 0). Whether minute bubbles are generated is determined based on the first measurement value measured in the first monitoring unit. As described above, if the first measured value is less than the effective value, it is determined that there is no state change in the RPE cells, and if it is more than the effective value, it is determined that the state change has started in at least one RPE cell.

On the other hand, when the user selects the treatment mode with the therapeutic intensity of the ASV 30, the treatment light repeats steps S120 to S140 until the first measured value exceeds the reference value corresponding to the ASV30. In this process, the controller 60 can determine, in real time, the specific gravity of the RPE cells in which the state change among the RPE cells at the target position has occurred, based on the first measured value measured in real time.

10A, it is determined that the first measurement value exceeds the reference value corresponding to the ASV 30 after the ninth treatment light is irradiated, and the controller 60 determines that the treatment is completed at the target position and stops the irradiation of the treatment light can do.

FIG. 10A shows a case where an abnormality is not detected during treatment, and FIG. 10B shows a case where abnormality is detected during treatment. Specifically, FIG. 10B shows a case where an abnormality is detected through the second monitoring unit 42 when the seventh treatment light is irradiated. In this case, the control unit immediately stops the treatment light irradiation at the point of time when the abnormality is detected, and terminates the treatment.

10A and 10B, in adjusting the parameters of the treatment light, the outputs of the treatment light are adjusted to be ramped to the same magnitude. However, as shown in FIG. 10C, if it is determined that the bubble is detected and the treatment end point is close, it is also possible to adjust the magnitude of the output of the treatment light to be smaller than before the minute bubble is detected.

On the other hand, FIGS. 5 and 10 show a method of increasing the output of the treatment light in controlling the parameters of the treatment light. However, this is an example, and it is also possible to control other parameters other than the output so that the magnitude of the energy transmitted per unit area by the treatment light may increase.

11 is a graph showing another example of adjusting the treatment light parameter. As shown in FIG. 11 (a), the treatment light generating unit generates the treatment light having the same pulse duration, and the parameter can be adjusted by gradually decreasing the off time between the treatment lights. Alternatively, as shown in FIG. 11 (b), the treatment light pulse having the same output can be generated, and the parameter can be adjusted so that the pulse duration of each treatment light gradually increases. In addition, as shown in FIG. 11C, the treatment light is irradiated so that each treatment light is composed of a plurality of unit pulses Pu, and the parameters are adjusted so that the number of unit pulses constituting each treatment light is sequentially increased It is possible.

In the above, the ophthalmic treatment apparatus for treating eye-like lesions such as the retina and its control method are described. However, the present invention can be applied to various ocular diseases by using various tissues in the eyeball as target positions as well as eye fundus lesions. As an example, the present invention can be applied to a treatment apparatus for treating glaucoma in the anterior segment and a control method thereof, which will be described below with reference to FIG.

12 is a cross-sectional view showing a state in which the anterior segment surface is treated using the present invention. Glaucoma is a lesion in which the optic nerve is damaged by the elevation of the intraocular pressure. The intraocular fluid is evacuated and the proper intraocular pressure is maintained. To this end, the ophthalmologic treatment apparatus according to the present invention can improve the discharging property of the fluid by irradiating therapeutic light on the trabecular meshwork (TM) tissue located below the Limbus of the anterior segment .

The ophthalmologic treatment apparatus according to Fig. 12, like the apparatus for treating the eye fundus lesion described above, carries out the treatment using the therapeutic light having the wavelength selectively absorbed into the melanoma. Like the RPE cells, the trabecular meshwork cell (TM cell), which constitutes the fibroblast tissue, contains pigment components such as melanocytes. Therefore, as the therapeutic light is irradiated, energy is transferred to the cells of the fibrous stem tissue, thereby causing thermal damage to the fibrous stem cells, thereby securing the discharge path of the fluid and maintaining the intraocular pressure normally.

In contrast to the ophthalmic treatment apparatus for treating the above-mentioned eye diseases, the treatment is performed by transferring energy to a plurality of RPE cells arranged at a target position with the retina as a target position. On the other hand, And the treatment is carried out by transferring energy to a plurality of fibrous scaffold cells arranged at a target position.

To this end, the alternative portion 70 of the ophthalmic treatment device comprises a contact lens including a reflective member. As a result, the path of various light including the therapeutic light is irradiated to the fiber main body tissue, which is the target position, through the reflecting member, and the reflected light reflected from the target position can also enter the beam delivery unit of the ophthalmic treatment apparatus through the reflecting member 71 have.

However, in addition to the structure of the alternative unit 70, the various control contents, including the construction and operation of the ophthalmic treatment apparatus described in the above embodiments, can be substantially applied to the ophthalmic treatment apparatus of Fig. Therefore, when treating glaucoma, the treatment light can be effectively irradiated to the plurality of fibroblast cells, and the optimal treatment can be controlled by effectively controlling the intensity of the treatment. The monitoring unit monitors the status information in different ways to effectively check the status information It is possible to implement an advantage of being able to stop urgently when an abnormality occurs.

In the foregoing, an ophthalmic treatment apparatus including two monitoring units and a control method thereof have been described in detail. It should be understood, however, that the above-described embodiments have been simplified for the sake of convenience of description and may be modified in various ways.

Claims (45)

A setting unit configured to set a treatment mode;
A treatment light irradiating unit for irradiating treatment light to the target position in the eye a plurality of times to perform treatment;
A monitoring unit for monitoring state information of the target position by the treatment light while the treatment light is irradiated; And
And a control unit for determining whether the treatment intensity according to the treatment mode has been reached using the information monitored by the monitoring unit and controlling the operation of the treatment light irradiation unit based on the result,
Wherein the monitoring unit includes a first monitoring unit for measuring state information of the target position in a first manner while the treatment light is irradiated and a second monitoring unit for measuring state information of the target position while the treatment light is irradiated, 2 < / RTI > mode,
Wherein the control unit determines whether or not the treatment intensity has been reached based on the information measured by the first monitoring unit and the second monitoring unit. The method according to claim 1,
The control unit adjusts the parameter of the treatment light when it is determined that the information detected by the monitoring unit does not reach the treatment intensity, and irradiates the treatment light to the target position when it is determined that the treatment intensity has been reached Wherein the treatment device is an ophthalmic treatment device. 3. The method of claim 2,
Wherein the control unit controls the parameter of the treatment light so that energy transmitted per unit area of the target position is increased by the treatment light when it is determined that the information detected by the monitoring unit does not reach the treatment intensity, Ophthalmic treatment devices. The method according to claim 1,
The treatment light is irradiated so as to have a spot size capable of transmitting energy to a plurality of cells located at the target position, and the plurality of cells are irradiated with a plurality of treatment lights to change the state of a part of cells Ophthalmic treatment device characterized by. 5. The method of claim 4,
Wherein the treatment light is irradiated so as to have a spot size that transfers energy to at least 10 or more cells. 5. The method of claim 4,
Wherein the treatment light is irradiated so as to have a spot size of 50 mu m or more and 1000 mu m or less in diameter at the target position. 5. The method of claim 4,
Wherein the therapeutic light is irradiated to the fundus and the plurality of cells are RPE cells located in the retina. 5. The method of claim 4,
Wherein the treatment light is irradiated to the lower side of a limbus of the anterior segment, and the plurality of cells are trabecular meshwork cells (TM cells). The method according to claim 1,
Wherein the monitoring unit senses a cell or tissue whose state changes by treatment among a plurality of cells or tissues disposed at a target position to which the treatment light is irradiated and monitors the progressed treatment intensity at the target position, Treatment device. The method according to claim 1,
Wherein the monitoring unit measures an acoustic signal generated while the tissue state of the target position is changed by the treatment light and measures the treatment intensity progressed to the target position. The method according to claim 1,
Wherein the monitoring unit includes a reflectometry sensor and measures the treatment intensity progressed to the target position using information of reflected light reflected from the target position. The method according to claim 1,
The monitoring unit irradiates the detection light to the target position to which the treatment light is irradiated, receives the detection light reflected from the target position, and measures the treatment intensity progressed to the target position using the interference information by the detection light Wherein the treatment device is an ophthalmic treatment device. The method according to claim 1,
And terminates irradiation of the treatment light to the target position when it is determined that the treatment intensity is reached by at least one of the information monitored by the first monitoring unit and the second monitoring unit. 14. The method of claim 13,
Wherein the first monitoring unit is an optoacoustic sensor and the second monitoring unit is a reflectometry sensor or an interferometry sensor. The method according to claim 1,
Wherein the setting unit is configured to display a plurality of treatment intensities having different values, wherein the user is configured to select a treatment intensity to set a treatment mode,
Wherein the treatment intensity displayed on the setting unit indicates a ratio of cells or tissues in which a state change occurs among a plurality of cells or tissues arranged at the target position. The method according to claim 1,
Wherein the setting unit is configured to display a plurality of treatment lesions so that a user selects a treatment lesion to set a treatment mode, wherein at least two of the treatment modes corresponding to the plurality of treatment lesions have different treatment strengths Wherein the treatment device is configured to perform the treatment. 17. The method of claim 16,
The setting unit is configured to display to a user a treatment mode for central serous chorioretinopathy (CSC) and a treatment mode for diabetic macular edema (DME)
Wherein the treatment mode for the central serous choroidopathy is configured to have a lower treatment intensity than the treatment mode for the diabetic macular edema. delete delete delete delete delete delete delete delete delete delete A curing light irradiating unit for irradiating curing light a plurality of times to a target position located in the eyeball;
A first monitoring unit for measuring the state information of the target position in a first manner while the treatment light is irradiated;
A second monitoring unit for measuring the state information of the target position while the treatment light is irradiated in a second mode different from the first mode; And
And a controller for adjusting parameters of the treatment light based on the information measured by the first monitoring unit and the second monitoring unit or determining whether to irradiate the treatment light. 29. The method of claim 28,
Wherein the first monitoring unit measures information on a treatment progress state or a treatment end point with respect to the target position and the second monitoring unit measures information on whether or not an abnormality occurs during the treatment, . 29. The method of claim 28,
Wherein the first monitoring unit measures state information of the target position by measuring an acoustic signal generated while the tissue state of the target position is changed by the treatment light,
Wherein the second monitoring unit receives reflected light reflected from the target position and determines whether an abnormality has occurred during the treatment. 29. The method of claim 28,
Wherein the control unit controls the parameter of the treatment light when the information sensed by the first monitoring unit is smaller than the first reference value and terminates irradiating the treatment light to the target position if the information is larger than the first reference value Ophthalmic treatment devices. 32. The method of claim 31,
Wherein the control unit terminates the treatment of the target position when the information sensed by the first monitoring unit is greater than the first reference value and proceeds the treatment by irradiating the treatment light to another target position. Device. 32. The method of claim 31,
Wherein the control unit immediately stops irradiating the treatment light regardless of information sensed by the first monitoring unit if the information sensed by the second monitoring unit is greater than a second reference value, . 34. The method of claim 33,
Wherein the control unit displays an abnormality occurrence on the outside through the notification unit if the information sensed by the second monitoring unit is larger than the second reference value. 34. The method of claim 33,
Wherein the first reference value is adjusted according to a treatment mode selected by the user, and the second reference value is a fixed value. 30. The method of claim 29,
Wherein the control unit controls the parameter of the treatment light so that energy transmitted per unit area of the target position is increased by the treatment light when the information sensed by the first monitoring unit is smaller than the first reference value, Wherein the irradiation of the treatment light is stopped and the treatment of the target position is terminated. 37. The method of claim 36,
Wherein the control unit controls the output of the treatment light to be sequentially increased when the information sensed by the first monitoring unit is smaller than the first reference value. delete delete delete delete delete delete delete delete

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