KR102343789B1 - Real-time radiation measuring system and method for measuring radiation in real-time - Google Patents

Abstract

In a real-time radiation measurement system and a real-time radiation measurement method using the same, the real-time radiation measurement system includes an implant, an imaging unit, and a control operation unit. The implant is positioned on the object to be photographed, and reacts to the radiation generated from the radiation therapy device and emits reactive light. The photographing unit includes three cameras positioned at three different positions with respect to the implant to photograph the reaction light. The control operation unit derives a dose distribution of radiation generated from the radiation therapy device based on the voxel value derived from the pixel value of the photographed image, based on the photographed images.

Description

Real-time radiation measurement system and real-time radiation measurement method using the same

The present invention relates to a real-time radiation measurement system and a real-time radiation measurement method using the same, and more particularly, by measuring the dose of radiation emitted from a radiation therapy device in real time, it is possible to obtain information on the amount of radiation that a patient is exposed to in real time. A real-time radiation measurement system and a real-time radiation measurement method using the same.

As the diagnosis and treatment technology using radiation develops, the use of radiation in the diagnosis and treatment of various patients is increasing. However, when the amount of radiation is increased, it causes a fatal problem to the human body, and as the use of radiation increases, management of the amount of radiation is becoming more important.

However, in radiodiagnosis or treatment of actual patients, it is very difficult to measure the current radiation dose, and the related technologies have not been accumulated until now.

For example, Korean Patent Registration No. 10-1669505 discloses measuring the radiation dose from a detector response measured during radiation irradiation in connection with a patient image as a technique for measuring the quality of radiation, but this is simply a measurement of radiation As an overview of the method has been disclosed, there is a limitation in that it is difficult to implement a technology for real-time radiation measurement.

In addition, Republic of Korea Patent No. 10-1900463 discloses a technique for dose measurement using X-ray-guided ultrasound, in which a target is placed inside a water-filled interior and the radiation dose is measured based on a change according to the thermal expansion of water. However, since it must be premised that the target is located inside the chamber filled with water, it is impossible to implement technology for real-time radiation measurement.

Accordingly, the implementation of a technology for measuring the dose of radiation to which a patient is irradiated in real time is required.

Republic of Korea Patent Publication No. 10-1669505 Republic of Korea Patent Publication No. 10-1900463

Accordingly, the technical problem of the present invention has been conceived in this regard, and an object of the present invention is to measure the dose of radiation emitted from a radiation therapy device in real time, thereby real-time radiation measurement that can obtain information on the amount of radiation that a patient is exposed to in real time. It's about the system.

Another object of the present invention relates to a real-time radiation measurement method using the radiation measurement system.

A real-time radiation measurement system according to an embodiment for realizing the object of the present invention includes an implant, a photographing unit, and a control operation unit. The implant is positioned on the object to be photographed, and reacts to the radiation generated from the radiation therapy device and emits reactive light. The photographing unit includes three cameras positioned at three different positions with respect to the implant to photograph the reaction light. The control operation unit derives a dose distribution of radiation generated from the radiation therapy device based on the voxel value derived from the pixel value of the photographed image, based on the photographed images.

In an embodiment, the implant may include a scintillating material.

In an embodiment, the reaction light is visible light, and the cameras may capture two-dimensional images of visible light, respectively.

In an embodiment, the control operation unit may include an image input unit receiving the captured images, dividing each of the images into predetermined pixels, and generating voxel values in division units based on pixel values of the divided pixels. a voxel value calculator that calculates each, a comparator that compares the divided pixel with a preset resolution, and a voxel value determiner that determines voxel values of a corresponding division unit as a final voxel value when the divided pixel has the same resolution as a preset resolution , and a radiation dose derivation unit for deriving the radiation dose distribution based on the final voxel value.

In an embodiment, when the one image is divided into n in the voxel value calculating unit, the number of division units in which the voxel values are calculated may be defined as n*3.

In an embodiment, the preset resolution may be less than or equal to a pixel value of the photographed image.

In an embodiment, the pixel value of each pixel may be determined in consideration of the effects of attenuation of light, refraction of light, and collision of light on a voxel value of the division unit corresponding to each pixel and a voxel value of an adjacent division unit. .

In an embodiment, coefficients in consideration of the effects of light attenuation, light refraction, and light collision may be derived based on the final voxel value and the final pixel value when the divided pixel has the same resolution as a preset resolution.

In an embodiment, the radiation dose derivation unit may derive the radiation dose distribution by inputting the final voxel value to a predefined voxel value and a radiation dose distribution curve.

In a real-time radiation measurement method according to an embodiment for realizing the object of the present invention, a radiation therapy device provides radiation to a subject in which an implant is located. The reaction light generated from the implant in response to the radiation is photographed using cameras located at three different positions. Based on the photographed images, a dose distribution of radiation generated from the radiation therapy device is derived based on voxel values derived from pixel values of the photographed image.

In one embodiment, the step of deriving the radiation dose distribution includes receiving the three photographed images, dividing each of the images into predetermined pixels, and based on the pixel values of the divided pixels each of the steps of calculating voxel values of a division unit, comparing the divided pixel with a preset resolution, and determining voxel values of a corresponding division unit as a final voxel value when the divided pixel is the same as a preset resolution , and deriving the radiation dose distribution based on the final voxel value.

In an embodiment, the calculating of the voxel values of the division unit may include dividing each of the images into a basic pixel unit, and calculating a voxel value of the basic division unit based on the pixel value of the basic pixel unit. The method may include the steps of, further dividing each of the basic pixel units, and calculating a voxel value of each division unit based on the pixel values of the additionally divided pixel units.

In an embodiment, the deriving the radiation dose distribution includes deriving a coefficient considering the effects of attenuation of light, refraction of light, and collision of light based on the final voxel value and the final pixel value; The method may include determining the final voxel value based on the final voxel value, and deriving the radiation dose distribution based on the final voxel value.

In an embodiment, in the step of deriving the radiation dose distribution, the radiation dose distribution may be derived by inputting the final voxel value to a predefined voxel value and a radiation dose distribution curve.

According to embodiments of the present invention, by including a scintillating material, an implant emitting visible light, which is a reaction light to radiation, is used as an implant during radiographic imaging, so that a radiation dose can be derived from a photographed image of visible light. do.

Therefore, it is possible to calculate the radiation dose simply by using only the photographed image of the implant, and it is possible to easily derive the radiation dose to be exposed during radiation treatment for the actual patient in real time.

In particular, in deriving the radiation dose based on the captured image, when the final voxel value in the final division unit is calculated, the radiation dose distribution can be easily derived through the predefined voxel value and the radiation dose distribution curve. The dose can be easily derived with high reliability.

In addition, in deriving a voxel value, by applying a so-called three-dimensional recon algorithm, it is possible to improve the easiness of calculation and the reliability of the calculation result.

1 is a schematic diagram illustrating a real-time radiation measurement system according to an embodiment of the present invention.
FIG. 2 is a flowchart illustrating a radiation measurement method using the radiation measurement system of FIG. 1 .
FIG. 3 is a flowchart illustrating a step of deriving a radiation dose distribution of FIG. 2 .
4 is an exemplary diagram for explaining a step of calculating a voxel value in two dimensions.
5 is an exemplary diagram for explaining a step of repeatedly calculating voxel values in two dimensions.
6A is a schematic diagram illustrating a step of dividing the basic pixel unit of FIG. 3 .
FIG. 6B is a schematic diagram illustrating a step of dividing into additional pixel units of FIG. 3 .
6C is a schematic diagram illustrating a step of determining whether the divided pixels of FIG. 3 have the same resolution as a preset resolution.

Since the present invention can have various changes and can have various forms, embodiments will be described in detail in the text. However, this is not intended to limit the present invention to the specific disclosed form, it should be understood to include all modifications, equivalents and substitutes included in the spirit and scope of the present invention. In describing each figure, like reference numerals have been used for like elements. Terms such as first, second, etc. may be used to describe various elements, but the elements should not be limited by the terms.

The above terms are used only for the purpose of distinguishing one component from another. The terms used in the present application are only used to describe specific embodiments, and are not intended to limit the present invention. The singular expression includes the plural expression unless the context clearly dictates otherwise.

In this application, terms such as "comprises" or "consisting of" are intended to designate that a feature, number, step, operation, component, part, or combination thereof described in the specification is present, but one or more other features It is to be understood that it does not preclude the possibility of the presence or addition of numbers, steps, operations, components, parts, or combinations thereof.

Unless defined otherwise, all terms used herein, including technical and scientific terms, have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. Terms such as those defined in commonly used dictionaries should be interpreted as having a meaning consistent with the meaning in the context of the related art, and should not be interpreted in an ideal or excessively formal meaning unless explicitly defined in the present application. does not

Hereinafter, preferred embodiments of the present invention will be described in more detail with reference to the accompanying drawings.

1 is a schematic diagram illustrating a real-time radiation measurement system according to an embodiment of the present invention.

Referring to FIG. 1 , a real-time radiation measurement system 10 (hereinafter, referred to as a radiation measurement system) according to the present embodiment includes an implant 300 , a photographing unit 400 , and a control operation unit 500 .

The radiation measurement system 10 measures the dose of radiation 110 incident from the radiation therapy device 100 to the patient, which is the object 200 to be photographed, and the implant 300 is the object 200 to be photographed. It is located on the to-be-photographed part of

In this case, the implant 300 includes, for example, a scintillating material, and is manufactured in a predetermined shape through 3D printing. It is obvious that the shape or structure of the prosthesis 300 may be variously modified according to the needs of radiographic imaging.

Meanwhile, as the implant 300 includes the scintillating material, the implant 300 emits reaction light in response to the incident radiation, and the reaction light may be visible light.

Accordingly, the photographing unit 400 photographs the reaction light emitted from the implant 300 , and in this embodiment, the photographing unit 400 includes first to third cameras located at three different positions. Including the fields 410, 420, and 430, three different images are taken.

That is, the first to third cameras 410 , 420 , and 430 photograph the reaction light, which is the visible light, at different positions, and immediately take a visible light image of the implant 300 .

In this case, the first to third cameras 410 , 420 , and 430 each take a two-dimensional image, and the respective captured images are mutually exclusive if the positions of the cameras are positioned perpendicular to each other in space. It may be a result of photographing in a vertical position, but since the cameras are generally located at arbitrary positions in space, the photographed images are two-dimensional images of the reaction light at a position in space where the camera is located. .

The control operation unit 500 ultimately derives a dose distribution of radiation based on the images captured by the photographing unit 400 , and through this, the amount of radiation finally incident to the object 200 . will acquire

In this case, the control calculation unit 500 includes an image input unit 510 , a voxel value calculation unit 520 , a comparison unit 530 , a voxel value determination unit 540 , and a radiation dose derivation unit 550 .

More specifically, the image input unit 510 receives images captured by the photographing unit 400 , and the voxel value calculating unit 520 divides each of the images into predetermined pixels, and divides each divided image into predetermined pixels. Each of the voxel values of the division unit is calculated based on the pixel value of the pixels, the comparator 530 compares the divided pixel with a preset resolution, and the voxel value determiner 540 determines whether the divided pixel is When the resolution is the same as the preset resolution, voxel values of the corresponding division unit are determined as the final voxel value, and the radiation dose derivation unit 550 derives the radiation dose distribution based on the final voxel value.

Hereinafter, detailed functions and operations of the control operation unit 500 will be described together with a radiation measurement method using the radiation measurement system 10 .

FIG. 2 is a flowchart illustrating a radiation measurement method using the radiation measurement system of FIG. 1 . FIG. 3 is a flowchart illustrating a step of deriving a radiation dose distribution of FIG. 2 . 4 is an exemplary diagram for explaining a step of calculating a voxel value in two dimensions. 5 is an exemplary diagram for explaining a step of repeatedly calculating voxel values in two dimensions. 6A is a schematic diagram illustrating a step of dividing the basic pixel unit of FIG. 3 . FIG. 6B is a schematic diagram illustrating a step of dividing into additional pixel units of FIG. 3 . 6C is a schematic diagram illustrating a step of determining whether the divided pixels of FIG. 3 have the same resolution as a preset resolution.

First, referring to FIG. 2 , in the radiation measurement method, the radiation 110 is irradiated from the radiation therapy device 100 to the object 200 on which the implant 300 is located (step S10 ).

Thereafter, the reaction light 310 generated from the implant 300 in response to the radiation 110 is photographed by the three first to third cameras 410 , 420 , and 430 located at different positions. (Step S20).

Thereafter, the control calculator 500 derives a radiation dose distribution based on three different two-dimensional images captured by the first to third cameras 410 , 420 , and 430 (step S30 ).

In this case, the derivation of the radiation dose distribution applies a so-called three-dimensional recon algorithm. Before describing the detailed application algorithm of the three-dimensional recon algorithm, with reference to FIGS. 4 and 5, the two-dimensional recon algorithm is applied. The algorithm is first described for convenience of explanation.

That is, it is assumed that the photographing unit 400 includes two cameras, and images photographed from the two cameras are input as shown in FIG. 4 .

In this case, the two cameras are positioned in a direction perpendicular to each other, and it is described for convenience of explanation that the two captured images are images perpendicular to each other, but substantially the two cameras are positioned in a direction that is not perpendicular to each other. In this case, the two photographed images correspond to the input images in a state where the angle θ between the two axis directions (X, Y) of FIG. 4 is not vertical but has a predetermined angle.

That is, the virtual voxel 630 shown in FIG. 4 has a square shape when the two cameras are perpendicular to each other, that is, when the input images are perpendicular to each other. If the angle θ is formed, that is, if the input image has a predetermined angle θ, it has a distorted quadrangular shape such as a rhombus shape.

In this way, even when the shape of the rectangle has a rectangular shape other than the square shape, the calculation of the following voxel values is the same. to explain

The first image 610 photographed by the first camera includes n pixels, and the second image 620 photographed by the second camera also includes n pixels.

In this case, in the two-dimensional recon algorithm according to the present embodiment, the first image 610 and the second image 620 having the n pixels are divided into basic pixel units. In this case, the basic pixel unit is 2, and accordingly, as shown in FIG. 4 , the first image 610 and the second image 620 are each divided into two pixels.

Thus, the first image 610 is converted into a first basic pixel 611 divided into two pixels, which is a basic pixel unit, and the second image 620 is also converted to a second basic pixel ( 621).

,

)은 상기 제1 이미지(610)의 픽셀값(

, ...,

)으로 연산되고, 상기 제2 기본 픽셀(621)의 각 픽셀의 값들(

,

)은 상기 제2 이미지(610)의 픽셀값(

, ...,

)으로 연산된다. At this time, the values of each pixel of the first basic pixel 611 (

,

) is the pixel value (

, ...,

), and values of each pixel of the second basic pixel 621 (

,

) is the pixel value (

, ...,

) is calculated as

은 하기 식 (1)로 연산될 수 있으며, 이와 동일하게 여타의 기본 픽셀의 픽셀값들이 연산될 수 있다. In this case, among the first basic pixels 611

can be calculated by Equation (1) below, and pixel values of other basic pixels can be calculated in the same way.

식 (1)

Equation (1)

,

,

,

)이 도출되면, 상기 도출된 픽셀값들로부터 하기 식 (2)를 이용하여, 상기 가상의 복셀(630)의 각 분할 단위의 복셀값들(

,

,

,

)을 도출할 수 있다. As described above, the pixel values (

,

,

,

) is derived, using Equation (2) below from the derived pixel values, voxel values (

,

,

,

) can be derived.

In this case, in the virtual voxel 630 defined as a two-dimensional square in two directions (X and Y), the first basic pixel 611 and the second basic pixel 621 each have two basic pixels. Since it is divided into units, it is divided into a total of four division units, and the four division units can be defined as basic division units.

,

,

,

)은, 상기 픽셀값들(

,

,

,

)과 하기 식 (2)의 관계를 가지며, 하기 식 (2)에서, 계수들이 정의된다면, 상기 복셀값들(

,

,

,

)의 도출이 가능하게 된다. That is, each voxel value of the mood division unit (

,

,

,

) is the pixel values (

,

,

,

) and Equation (2) below, and if coefficients are defined in Equation (2) below, the voxel values (

,

,

,

) can be derived.

Equation (2)

,

,

,

)의 도출을 위해서는, 상기 계수들(

)이 정의되어야 하는데, 상기 계수들은 실제 방사선 조사 및 이에 대한 반응광의 방사에 따라 다양하게 변경될 수 있다. Meanwhile, in Equation (2), the voxel values (

,

,

,

) for the derivation of the coefficients (

) should be defined, and the coefficients may be variously changed according to the actual radiation irradiation and the radiation of the reaction light thereto.

Therefore, in this embodiment, in order to derive the voxel values from Equation (2), after inputting the coefficients as arbitrary initial values, the values of the coefficients are changed until Equation (2) is satisfied. A coefficient that finally satisfies Equation (2) may be derived by performing an iterative operation, and the voxel values may be derived based on this.

However, as will be described later, in the present embodiment, since the voxel value in Equation (2) does not correspond to the voxel value to be finally derived, the formula ( From the equation 2), iterative work for deriving the coefficients may be performed, and a final voxel value may be derived therefrom.

, 굴절이나 충돌과 같은 부수적인 영향을 나타내는 계수

및

가 있다. At this time, in the coefficient, a coefficient indicating the effect of attenuation of light

, a coefficient representing an incidental effect such as refraction or collision

and

there is

That is, through Equation (2), a relational expression between a pixel value in a basic pixel unit and a voxel value in a basic division unit may be derived, but such division in a pixel unit is repeatedly performed.

As shown in FIG. 5, each pixel of the first basic pixel 611 divided into two is divided into two again, and the first image 610 is divided into four pixels, and similarly, the first image 610 is divided into four pixels. 2 The image 620 is also divided into 4 pixels.

Through this, each of the basic division units 631 , 632 , 633 , and 634 obtained by dividing the virtual voxel 630 into quarters is further further divided into 4, and the virtual voxel 630 divided into 16 is divided into 4 equal parts. For each division unit, the above operation is repeatedly performed.

,

, ...),(

,

, ...)을 연산하고, 마찬가지로 식 (2)와 유사한 방법을 통해, 상기 픽셀값들과 상기 복셀값들(

,

,

,

, ...)의 관계식을 도출할 수 있다. That is, as in Equation (1), for each of the pixels divided into the four pixels, the pixel values (

,

, ...),(

,

, ...), and similarly, through a method similar to equation (2), the pixel values and the voxel

,

,

,

, ...) can be derived.

)은 상기 임의의 초기값으로부터 시작하여 상기 관계식을 만족시키기 위한 최적의 계수들을 반복(iteration)을 통해 도출할 수 있고, 이를 통해, 상기 복셀값들을 도출할 수 있다. In addition, the coefficients included in the relation (

) can start from the arbitrary initial value and derive optimal coefficients for satisfying the relational expression through iteration, and through this, the voxel values can be derived.

The division of pixels and thus division of virtual voxels are repeatedly performed, and the repetitive division is performed until the divided pixels have the same resolution as a preset resolution.

In this case, the resolution may be set in advance by the user, and may be set to be less than or equal to the resolution of each of the cameras 410 , 420 , and 430 . That is, if the resolution of each of the cameras is 1024*768, the preset resolution may be set to a resolution of 1024*768 or less, and accordingly, the number of divided pixels is the same as the preset resolution. If it loses, segmentation for the pixel is stopped.

)이 포함된 식으로 도출될 수 있다. 이 때, 최종 분할된 픽셀의 개수가 P개라고 한다면, 상기 분할된 복셀들의 개수는 P*P개(2차원 이므로)로 정의된다. Thus, if pixel values of each pixel in the last segmented pixel are defined as final pixel values, and thus voxel values of each voxel of the finally segmented virtual voxel 630 are defined as final voxel values, In the same way as in Equation (2), the relationship between the final pixel values and the final voxel values is

) can be derived as In this case, if the final number of divided pixels is P, the number of divided voxels is defined as P*P (because it is two-dimensional).

)을 반복(iteration)을 통해 최적 계수를 도출할 수 있으며, 이를 통해 상기 최종 복셀값들을 도출할 수 있다. 즉, 상기 가상의 복셀(630)의 P*P개의 각각의 복셀들의 복셀값들이 도출된다. Thus, likewise in the final derived equation, the coefficients (

) can be derived through iteration, and the final voxel values can be derived through this. That is, voxel values of each of the P*P voxels of the virtual voxel 630 are derived.

The two-dimensional recon algorithm described above is expanded and applied to a three-dimensional recon algorithm in the step of deriving the radiation dose distribution in the control calculation unit 500 in this embodiment.

In this case, since the 3D recon algorithm is conceptually the same as the 2D recon algorithm except for using one additional image as one more dimension is added, a description using a detailed formula will be omitted.

More specifically, in the step of deriving the radiation dose distribution in the control operation unit 500 to which the 3D recon algorithm is applied, first, referring to FIG. 3 , the first to third cameras 410 , 420 , 430 . The three different images each captured in are input to the image input unit 510 (step S31).

6A to 6C, as described with reference to FIGS. 4 and 5, three cameras are positioned in a direction perpendicular to each other, and the three captured images are perpendicular to each other. The three cameras may be positioned in a direction that is not perpendicular to each other, and in this case, the captured images are input while being inclined at a predetermined angle to each other.

That is, the virtual voxel 750 shown in FIGS. 6A to 6C has a square shape when the three cameras are perpendicular to each other, that is, when the input images are perpendicular to each other, but the three cameras If they are not perpendicular but form a predetermined angle with each other, they have a shape like a crushed cube.

Thereafter, each of the images is divided into basic pixel units having a 3*3 matrix (step S32).

The images taken by each of the first to third cameras 410, 420, and 430 may include n pixels, and in the 3D Recon algorithm in this embodiment, each of the images is converted into a basic pixel unit. Split. In this case, the basic pixel unit is 3, and accordingly, each of the images is divided into 9 pixels to have a 3*3 matrix, that is, as shown in FIG. 6A .

Thus, the first image photographed by the first camera is converted into a first basic pixel 710 divided into 3*3 (9) pixels, and the images photographed by the second camera and the third camera are similarly It is converted into a second basic pixel 720 and a third basic pixel 730 , respectively.

Meanwhile, as the pixels are divided as described above, the virtual voxel 750 is divided into 9*3 (27) basic unit blocks 751, 752, ... as shown in FIG. 6A. is divided

Then, based on the relational expression between the pixel values of the basic pixel unit and the voxel values of the basic division unit, voxel values of each of the divided voxels are calculated (step S33).

That is, similarly to Equation (1) in the above 2D Recon algorithm, the pixel value of each divided pixel of each of the first to third basic pixels 710 , 720 , and 730 may be obtained.

Also, between the pixel value of each pixel and the voxel value of each voxel of the voxel 750 divided into 27 pieces, the above-described Equation (2) can be derived in three dimensions.

) 역시, 2차원 리컨 알고리즘과 동일한 반복(iteration) 방법으로 도출될 수 있다. Accordingly, similarly to the 2D Recon algorithm, the respective voxel values may be derived from the relational expression between the pixel values and the voxel values. In this case, the coefficients (

) can also be derived by the same iteration method as the two-dimensional Recon algorithm.

Thereafter, as shown in FIG. 6B , each unit pixel of the first to third basic pixels 710 , 720 , and 730 is further divided into 3*3 pixels again (step S34 ).

In addition, according to the additional division of the pixel, the virtual voxel 750 is further divided to match each pixel, and accordingly, each of the basic unit blocks 751 , 750 , ... is 9*3 again. It is further divided into (27) blocks (voxels).

)을 포함한 관계식으로 정의될 수 있으며, 이를 통해, 상기 복셀값들을 개별적으로 도출할 수 있다. Thereafter, the pixel value of each of the additionally divided pixels and the voxel value of each of the additionally divided voxels are similarly calculated by the coefficients (

) may be defined as a relational expression including ), and through this, the voxel values may be individually derived.

The division of pixels and thus division of virtual voxels are repeatedly performed (steps S34 and S35), and the repetitive division is performed until the divided pixels have the same resolution as a preset resolution (step S36). .

In this case, as described above, the resolution may be set in advance by the user, and may be set to be less than or equal to the resolution of each of the cameras 410 , 420 , and 430 . That is, if the resolution of each of the cameras is 1024*768, the preset resolution may be set to a resolution of 1024*768 or less, and accordingly, the number of divided pixels is the same as the preset resolution. If it loses, segmentation for the pixel is stopped.

)이 포함된 식으로 도출될 수 있다(단계 S37). Thus, the pixel values 770 , 780 , and 790 of each pixel in the final divided pixel are defined as the final pixel value, and thus voxel values of the respective voxels of the finally divided virtual voxel 750 are defined. When defined as final voxel values, in the same way as in Equation (2), the relationship between the final pixel values and the final voxel values is determined by the coefficients (

) can be derived in an expression including (step S37).

)을 반복(iteration)을 통해 최적 계수를 도출할 수 있으며, 이를 통해 상기 최종 복셀값들을 도출할 수 있다(단계 S38). Thus, likewise in the final derived equation, the coefficients (

) can be derived through iteration, and the final voxel values can be derived through this (step S38).

In this case, the derived voxel values mean the intensity of light in each voxel of the virtual voxel 750 , that is, the intensity of reaction light reacted by the implant 300 .

In the case of the so-called three-dimensional recon algorithm described above, the two-dimensional recon algorithm described above is expanded in three dimensions, and even if the vertical applied to the two-dimensional recon algorithm is expanded in three dimensions, it is within the range apparent to those skilled in the art. Since a related formula can be derived, a description of a lengthy and repeated formula will be omitted.

Meanwhile, when the final voxel value is determined based on the final pixel value as described above (step S38), a radiation dose distribution is derived based on the final voxel value (step S39).

In this case, for the radiation dose distribution, a predefined voxel value and a radiation dose distribution curve may be applied. Accordingly, a radiation dose matching the final derived voxel value is derived to derive the final radiation dose distribution. be able to do That is, the radiation dose in each of the unit voxels of the virtual voxel 750 can be derived.

Through this, the user is provided with the implant 300 based on the radiation dose distribution of the virtual voxel 750 in contrast to the implant 300 based on the reaction light reacted from the implant 300 . , that is, the radiation dose distribution provided to the object 200 can be checked.

On the other hand, the predefined voxel value and the radiation dose distribution curve are predefined by the user and can be input through a separate database (not shown). By setting the coefficient, the voxel value and the radiation dose distribution curve can be easily defined.

According to embodiments of the present invention, by including a scintillating material, an implant emitting visible light, which is a reaction light to radiation, is used as an implant during radiographic imaging, so that a radiation dose can be derived from a photographed image of visible light. do.

Thus, it is possible to calculate the radiation dose simply by using only the photographed image of the implant, and it is possible to easily derive the radiation dose to be exposed during radiation treatment to the actual patient in real time.

In particular, in the derivation of the radiation dose based on the photographed image, when the final voxel value in the final division unit is calculated, the radiation dose distribution can be easily derived through the predefined voxel value and the radiation dose distribution curve. The dose can be easily derived with high reliability.

In addition, in derivation of the voxel value, by applying a so-called three-dimensional recon algorithm, it is possible to improve the easiness of calculation and the reliability of the calculation result.

Although the above has been described with reference to the preferred embodiment of the present invention, those skilled in the art can variously modify and change the present invention without departing from the spirit and scope of the present invention as set forth in the following claims. You will understand that you can.

10: radiation measurement system 100: radiation therapy device
200: object to be photographed 300: implant
310: reaction light 400: photographing unit
500: control operation unit 510: image input unit
520: voxel value calculation unit 530: comparison unit
540: voxel value determining unit 550: radiation dose derivation unit

Claims (14)

an implant positioned on the object to be photographed and emitting reactive light in response to radiation generated from the radiation therapy device;
a photographing unit including three cameras positioned at three different positions with respect to the implant to photograph the reaction light; and
Based on the captured images, based on the voxel value derived from the pixel value of the photographed image, comprising a control calculation unit for deriving a dose distribution of the radiation generated from the radiation therapy device,
The control operation unit,
an image input unit receiving the photographed images;
a voxel value calculating unit that divides each of the images into predetermined pixels and calculates voxel values of each division based on the pixel values of each divided pixel;
a comparator for comparing the divided pixels with a preset resolution;
a voxel value determiner configured to determine voxel values of a corresponding division unit as final voxel values when the divided pixels have the same resolution as a preset resolution; and
and a radiation dose derivation unit for deriving the radiation dose distribution based on the final voxel value. According to claim 1, wherein the prosthesis,
A real-time radiation measurement system comprising a scintillating material. According to claim 1,
The reaction light is visible light, and the cameras capture two-dimensional images of visible light, respectively. delete The method of claim 1, wherein the voxel value calculator comprises:
When the single image is divided into n pieces, the division unit in which the voxel values are calculated is defined as n*3 units. According to claim 1, wherein the preset resolution,
A real-time radiation measurement system, characterized in that it is less than or equal to the pixel value of the photographed image. According to claim 1, wherein the pixel value of each pixel,
The real-time radiation measurement system according to claim 1, wherein the determination is made in consideration of the effects of attenuation of light, refraction of light, and collision of light on the voxel value of the division unit corresponding to each pixel and the voxel value of the adjacent division unit. The method of claim 7, wherein the coefficients considering the effects of attenuation of light, refraction of light, and impact of light,
The real-time radiation measurement system, characterized in that it is derived based on the final voxel value and the final pixel value when the divided pixels have the same resolution as a preset resolution. The method of claim 1, wherein the radiation dose derivation unit,
A real-time radiation measurement system, characterized in that the radiation dose distribution is derived by inputting the final voxel value to a predefined voxel value and a radiation dose distribution curve. A radiation therapy device comprising: providing radiation to a subject in which the implant is located;
photographing the reaction light generated from the implant in response to the radiation using cameras located at three different positions; and
Based on the photographed images, based on the voxel value derived from the pixel value of the photographed image, comprising the step of deriving a dose distribution of the radiation generated from the radiation therapy device,
The step of deriving the radiation dose distribution comprises:
receiving the three captured images;
dividing each of the images into predetermined pixels, and calculating voxel values in division units based on pixel values of each divided pixel;
comparing the divided pixels with a preset resolution;
determining voxel values of a corresponding division unit as final voxel values when the divided pixels have the same resolution as a preset resolution; and
and deriving the radiation dose distribution based on the final voxel value. delete 11. The method of claim 10, wherein calculating each of the voxel values of the division unit comprises:
dividing each of the images into basic pixel units;
calculating a voxel value of a basic division unit based on the pixel value of the basic pixel unit;
further dividing each of the basic pixel units; and
and calculating a voxel value of each division based on the pixel values of the additionally divided pixel units. 11. The method of claim 10, wherein deriving the radiation dose distribution comprises:
deriving coefficients in consideration of the effects of attenuation of light, refraction of light, and collision of light based on the final voxel value and the final pixel value;
determining the final voxel value based on the derived coefficient; and
and deriving the radiation dose distribution based on the final voxel value. 14. The method of claim 13, wherein in the step of deriving the radiation dose distribution,
A real-time radiation measurement method, characterized in that the radiation dose distribution is derived by inputting the final voxel value to a predefined voxel value and a radiation dose distribution curve.

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