KR101030927B1 - Radiation dosimetry method depending on patient and system thereof - Google Patents

Abstract

The present invention relates to a method and system for measuring radiation by calculating an effective calibration value of a systemic counter to measure the internal exposure of a radioactive material. Radiation measuring system of the present invention, a three-dimensional image forming unit for forming a three-dimensional image based on the optical image of the subject knowing the radiation intake; A computer simulation unit for performing computer simulation on the 3D image; A coefficient correction unit for calculating a telegraph counter counting efficiency for the computerized 3D image and performing coefficient correction on the 3D image using the counting efficiency; And a dose measuring unit for measuring a radiation exposure dose with respect to the coefficient-corrected 3D image.

3D image, voxel phantom, internal exposure, telegraph, dose assessment

Description

RADIATION DOSIMETRY METHOD DEPENDING ON PATIENT AND SYSTEM THEREOF

The present invention relates to a method and system for measuring internal exposure dose, and more particularly, to a method and system for measuring radiation by calculating an effective calibration value of a systemic counter for measuring the internal exposure of a radioactive material.

The method of quantitatively evaluating radioactive substances in the human body includes direct bioassays for directly measuring external radioactivity in the body, indirect bioassays for analyzing and evaluating samples taken from living bodies such as in vivo bioassay or urine, and It is roughly classified as an in vitro bioassay. Because direct bioassay can be applied only when the radiation emitted by the radionuclides in the body can be measured outside the body, gamma rays or characteristic X-rays, or high-energy photons, are the main targets. It is common to use indirect bioassays for alpha emitters or beta emitters, for which emission radiation cannot be measured in vitro.

Direct bioassay is a low-level radiometric method that measures a small amount of radioactivity in a large measurement object called a human body with a detector at a considerable distance from the measurement object. Therefore, counting efficiency is a major factor in determining the performance of the method. Photons emitted from radionuclides in the body have low geometrical efficiency due to the distance of several tens of centimeters to the detector, and inherently low counting efficiency because they are attenuated by human tissue material, air, and body window incident window materials to the body counter. .

Factors that determine the minimum detectable activity (MDA) that can be measured in low-level radiometric measurements are counting efficiency, background counting rate, and counting time. In order to measure the trace radioactivity in the body, the MDA must be lowered. To this end, the counting efficiency must be increased, the background count must be lowered, and counting time must be increased. Increasing the counting time is limited due to practical limitations such as inconvenience of the subject. To reduce the background coefficients, passive shielding enhancements and active asynchronous clock (or simultaneous) techniques are used. To increase the counting efficiency, increase the size of the detector and if possible close the detector to the detector.

Assuming that the best techniques for lowering the MDA are used, ultimately the counting efficiency should be determined for a given measurement condition. This process is called calibration of the counter. In general, the counter calibration efficiency is determined by measuring a sample (standard source) having known radioactivity under conditions similar to those of the actual measurement target.

If the human body is to be measured, the standard source used for calibration should be similar in shape and size to the human body. Therefore, for the calibration of the counter for body count, a doll measuring object with known radioactivity is used. Such doll objects are called objects or phantoms. However, unlike general laboratory measurements, the measurement object is not formalized in the case of body coefficient. This is because the individual's physique or body type differs from person to person. Therefore, in principle, it is necessary to have an object that corresponds to various types of human body and to have a counting efficiency set by measuring each of them. For example, subjects have been developed and used for applications where the physique differs significantly, such as adults and children.

The most common BOMAB object (see Figure 3), which has been used since the early days of human dosimetry, forms a doll shape by filling a radioactive solution into several cylindrical or elliptical containers shaped to the body or limbs, and the object family specification by age group. It is determined by processing. Kovtun et al. Developed a model for constructing family simulations by combining polyethylene cubes of various specifications [ Radiat. Prot. Dosim. 89 (3-4) .239-242 (2000)] Carlan et al. Radiat. Prot. Dosim. 116 (1 ?? 4), 160 ?? 164 (2005)] IGOR objects based on this model have been developed and used. Representatives of the object closer to the human body is RANDO phantom [ Am. J. Rentg. 87, 185 (1962)]. The RANDO phantom uses isocyanate rubber for soft tissue, light material based on epoxy resin, and actual bone for bone. Subjects modeled to the internal organ shape for the torso, the main area of interest in anthropometric measurements, include the JAERI torso phantom [ J. Nucl. Sci. Techol . 25, 875 (1988)] and Livermore Torso Phantom [ Proc. 6th IRPA , 964 (1984)].

Despite these developments, there are some problems in using subjects to calibrate the counter and using them to determine intake [ Radiat. Prot. Dosim. 128 (2). 245-250 (2008). The first is that the size and shape of a person as a subject vary considerably to represent a standard subject. Although there are different groups with intrinsic physique differences between adults and children, there may be significant differences in the geometrical arrangement of measurements and even the counting efficiency, depending on body type.

Second, there is a problem of determining which data to use for the actual subject's physique even when there are data corrected using more various objects. In addition, the actual radioactivity in the body is heterogeneously distributed according to the nuclide and its physicochemical form, but there is a problem that it is difficult to reflect such nonuniform characteristics in the subject.

Therefore, it is necessary to secure a more appropriate counting efficiency data set considering various subject sizes in order to improve these problems caused by the size and shape of subjects in direct bioanalytical measurement for internal exposure evaluation. The primary approach to determining efficiency data for different types of physique is to have a set of real objects with such a specification and make calibration measurements for each. For this purpose, family mock-ups have been developed and used that reflect physique differences according to age groups, but in the case of adults, it is practically difficult in terms of cost and maintenance to have subjects that faithfully reflect wide body differences. One alternative to this is to replace actual measurements with sophisticated simulation calculations. Since transport calculations for photons, interactions with detector materials, and simulation tools have been developed, such means can be used to evaluate the efficiency data of body counters without satisfactory measurements. The real phantom will then be sufficient as a representative one to use to demonstrate that the efficiency data from the simulation is adequate.

The present invention provides a method and system for measuring radiation by calculating an effective calibration value of a systemic counter to measure the internal exposure of a radioactive material.

The radiation measuring system of the present invention includes a three-dimensional image forming unit for forming a three-dimensional image based on an optical image of an object having known radiation intake; A computer simulation unit for performing computer simulation on the 3D image; A coefficient correction unit for calculating a telegraph counter counting efficiency for the computerized 3D image and performing coefficient correction on the 3D image using the counting efficiency; And a dose measuring unit for measuring a radiation exposure dose with respect to the coefficient-corrected 3D image.

Radiation measuring method of the present invention comprises the steps of: a) forming a three-dimensional image based on an optical image of a subject with known radiation intake; b) performing computer simulation on the 3D image; c) calculating the systemic counter counting efficiency for the computerized 3D image; d) performing coefficient correction on the 3D image using the coefficient efficiency; And e) measuring a radiation exposure dose with respect to the coefficient corrected three-dimensional image.

According to the present invention, the front and side pictures can be taken using a digital camera to reconstruct the object into a 3D image using the boundary values of the object and the background. And. The object image reconstructed in 3D may be converted into an input file of MCNPX and used for computer simulation.

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings. In the following description, well-known functions or constructions will not be described in detail if they obscure the subject matter of the present invention.

1 is a block diagram showing the configuration of a patient-specific radiation measurement system according to an embodiment of the present invention, Figure 2 is an exemplary view showing the configuration of a radiation measurement system according to an embodiment of the present invention, Figure 3 An illustration of a BOMAB object assuming a human body according to an embodiment.

Referring to FIG. 1, the patient-specific radiation measuring system 100 according to the present invention includes a three-dimensional image forming unit 110 and a three-dimensional image forming a three-dimensional image based on an optical image of an object for which radiation intake is already known. Computational simulation unit 120 for performing a computer simulation for the computerized, calculating the coefficient efficiency of the whole body counter for the computerized three-dimensional image, coefficient correction unit 130 for performing the coefficient calibration using the coefficient efficiency and the coefficient correction It includes a dose measuring unit 140 for measuring the radiation dose to the three-dimensional image.

The present invention looks at a method of using computer simulation for a subject who already knows the radioactive intake to evaluate a patient-specific internal exposure dose. The camera required for photographing the object of the present invention is about 300,000 pixels. However, a camera that can clearly distinguish colors should be used. First, the camera is fixed to be positioned at a specific distance from the object. Since the camera moves when the camera shutter is pressed, the camera is operated using a remote control. When the camera is fixed, place the object on a rotating plate that can rotate 360 degrees. The rotating plate is used to accurately measure angles when photographing the front and side surfaces of an object. If two cameras are used, one can be installed in the front direction and the side direction of the object and photographed. When using two cameras, not only the angle but also the distance to the object and the height where the camera is installed should be considered. Just like taking a picture with one camera, two cameras should be installed at the same height and the same distance from the object. When photographing the object, the background should be made of a material that does not reflect light well in a color that can be clearly distinguished from the boundary of the object. This is because a 2D silhouette of the object is required to reconstruct the object into a 3D image (volume object) using a camera. Inadequate background makes it difficult to distinguish between the background and the object.

In this embodiment, LABVIEW 8.2 was used to code a program for reconstructing a 3D volumetric object from an optical image of the object taken from the front and side. Each optical image includes a two-dimensional array and the elements of each array contain color information. When an optical image of 5 million pixels is expanded into a three-dimensional array, an array containing about one billion elements is formed. This arrangement requires a significant amount of computer memory and increases the computation time, so we use optical images with a pixel count of 500 x 500. In this embodiment, the optical image is photographed at 5 million pixels, and then reduced to 250,000 pixels.

In this embodiment, the background except for the object in the optical image is removed as much as possible to improve the operation speed by using less memory. The method of removing a background except an object uses a method of cutting an array using a function. The area to be removed from the optical image can be arbitrarily set by the user, but the same portion must be removed from the front and side optical images. Preprocessing for the optical image may reduce memory usage by removing unnecessary images such as a background from the optical image and reducing the number of pixels.

When the optical image of the object was taken, the image was taken to be distinguished from the background. Therefore, the object and the background can be easily separated by setting a range of a specific array value in the array and recalling only a predetermined range of arrays. Figure 4 is an exemplary view showing an image separated from the background in the optical image according to an embodiment of the present invention. The color information of the array elements included in the optical image may be searched, and logical arrays may be used to separate array elements having color information of the array elements different by a predetermined value or more. While the array elements are separated, the boundary elements of the object and the array elements inside the object are set to have a value of "1", and the array elements of the background portion are set to have a value of "0". These two-dimensional arrays overlap each other to form a three-dimensional array. For example, if the matrix position of (3,5) has a value of "1" representing the inside of the object boundary, the process of converting the two-dimensional matrix into a three-dimensional matrix is (3,5,0), (3, Simply repeat the values of 5,1), (3,5,2), (3,5,3), ..., (3,5,600) and iterate over all the values in the two-dimensional array. A layered form, that is, a three-dimensional array, is formed. A three-dimensional array of two front and side optical images is formed, and a three-dimensional array of side optical images is rotated 90 degrees by a rotation matrix to form a side rotation array. For example, when sculpting a three-dimensional sculpture, it is similar to the concept of forming a three-dimensional sculpture, starting with the material of the cube and digging out the sketch on the front and side, and the parts outside the sketch. That is, a three-dimensional array can be formed using two-dimensional array information of the front and side by using a concept of creating a three-dimensional object by the sum of two-dimensional information.

The coding of the rotating part recognizes the matrix number as the coordinate and inputs the value before the rotation to the coordinate passed through the rotation matrix. If the 3D array of the front optical image and the side rotation array are added to find an array having a value of 2, a 3D image satisfying the front and side optical images may be formed.

5 is an exemplary view showing an object reconstruction program according to an embodiment of the present invention. The object reconstruction program was coded to confirm the process of constructing the cross section. In the "Count" area at the bottom right, it is possible to check the number of cross sections of the object, and the corresponding cross section is displayed on the left side. The area indicated in light color satisfies the cross section formed by each optical image, and the area indicated in dark color satisfies the cross section formed by the front and side optical images. In coding for forming a three-dimensional array of objects, the utilization of dynamic memory is important. For example, a method of dividing a three-dimensional array into a predetermined size without calculating all at once can be used.

The reconstructed three-dimensional image that satisfies the front and side optical images includes a rectangular cross section. However, since the cross section of the actual object is composed of many curves, the human body can be more accurately simulated by converting the rectangle into an ellipse. Set the long side of the rectangle to be the long axis of the ellipse, and the short side to be the short axis of the ellipse. Specifically, the coding method is set such that the long side is shorter and the shorter one is the difference between the maximum value and the minimum value of the row number and the difference between the maximum value and the minimum value of the column number among the array sets satisfying the logical operation in the row and column. You can also find the center of the ellipse by adding the column number with the minimum value and the row number with the minimum value to the column number difference and the row number difference. Certain cross-sections of the human body include parts that are not close to each other, such as the arm and torso, so it must be coded to find a number of center points in the process of finding the center point. Since the optical image of the object contains a number of rectangles, it must be able to distinguish non-contiguous rectangles, and noise is regarded as noise if the short axis does not contain at least three array elements while noise, or small ellipses, occurs during image processing. To be deleted.

6 is a cross-sectional view of a reconstructed three-dimensional image according to an embodiment of the present invention, noise generation, and volume increase of an arm portion. The increase in volume of the arm occurs because the arm is included in the body in an algorithm that uses the interface between the object and the background. The reconstructed 3D image has a sitting height difference of about 4-5cm compared to the real one, the volume of the arm increases, and the thigh simulation is inaccurate. The sitting height is 4-5cm smaller than the real thing because it defines the voxel by weight first. For example, the definition of a voxel is the same as that of the optical size alone, which does not easily define the actual size. To measure the actual size of an object in the picture, you can use a ruler that knows the exact size. However, in the present embodiment, it is determined that it is important to accurately describe the volume of the entire voxel, that is, the weight, rather than the geometrically accurate 3D image, thereby defining the size of the voxel based on the weight. The specific method will be described later. The completeness of the reconstructed three-dimensional image can only be judged by the naked eye.

7 is an exemplary view showing a result of reconstructing an adult male object into a 3D image, and it is determined that the object is accurately reconstructed into a 3D image. Since the present invention aims to finally apply to the human body, it can be seen that the same applies to the human body as shown in FIG. 9 is an exemplary view showing an optical image of a BOMAB object family proposed for verification and a reconstruction image using the same. It can be seen that the method proposed in the present invention satisfies several kinds of objects. In FIG. 9, (a) is an adult subject, (b) is an adult female subject, (c) is a 10 year old child subject, (d) is a 4 year old child subject, and each reconstructed three-dimensional image. In the adult female and male subjects, since the reconstructed three-dimensional images showed little difference, the three-dimensional images of the female subjects were omitted. Verification that satisfies various kinds of objects is a method of easily grasping the value of the present invention, and specific verification values will be described later.

Monte Carlo simulation is a means of replacing the unexplored parts of radiation. In other words, the results can not be confirmed through experiments, but if you perform similar experiments by implementing similar experiments with computer simulations, the results of transcription simulations for the untestable parts will be obtained. In the present embodiment, the shape of the human body is photographed by a camera to form a three-dimensional image, the coefficient efficiency is calculated using the computerized three-dimensional image, and the coefficient correction is performed using the coefficient efficiency. This can be replaced by comparing different types of objects because they cannot be verified using the human body. The computer simulation unit 120 may perform computer simulation by merging a predetermined number of surrounding volume elements in order to improve a simulation execution speed during computer simulation of a 3D image. For example, Monte Carlo N-Particle eXtended (MCNPX) may be used for the computer simulation.

When the object is reconstructed using the front and side optical images, the size of the object can be calculated by multiplying the actual size of one element when the number of elements corresponding to the short axis and the long axis of the ellipse is determined and the matrix number of the central position is determined. have. That is, multiplying the length of one side of a cube-shaped voxel by the number of voxels from the head to the toe of the object may determine the size of the object. In addition, the volume of the object may be calculated using the number of voxels used to construct the object. This enables MCNPX simulation by defining the position of the object physically and accurately in the virtual space. For example, as a method for determining the size of a voxel, there is a method of preparing a criterion such as a ruler when capturing an optical image of an object. However, in the present embodiment, the voxel size is set to the actual size in order to measure the weight of the subject so that the reconstructed 3D image has the correct weight. There is an advantage that it is easier to measure the weight of the object than the process of adjusting the scale with the object, and the reconstructed three-dimensional image has the advantage of having the correct weight. Since the radiation measuring system 100 corrects an object made of water such as BOMAB, the reconstructed three-dimensional image is also made of water, and then, the weight of the object is changed to fatigue and the volume of the object is a voxel including the reconstructed three-dimensional image. Divide by the number. The square root of this value can be calculated to calculate the length of one side of the voxel.

To define the actual size of the reconstructed 3D image, the actual position of the object must be defined in the virtual space. Lead simulation chairs and counter collimators are always defined under the same conditions in computer simulations, so they need to be defined only once in the input data, but the reconstructed three-dimensional images have values that change according to the target, so they need to be corrected to ensure correct positioning. Furthermore, in this embodiment, the camera position is used differently according to the object, so it must be checked carefully. The method of checking the data about the coordinates is to check whether the center of the torso is in line with the center of the counter, whether the pelvis is in close contact with the chair, whether the back of the torso is in close contact with the chair back, and MCNPX. There is a method using a commercial program that can identify the geometric shape of the.

FIG. 10 is an exemplary view showing how a 3D image reconstructed using X_Deep_32 4.0 is defined in an input file. The reconstructed 3D image is composed of a plurality of voxels, but computer simulation can be performed more easily and quickly by generating an input file using the characteristics of voxels in an ellipse. That is, the repetition of the ellipse is not the repetition of the cube. In computer simulation, radiation is emitted from all positions of cells that contain information about the voxel and define the position inside the object of the voxel to simulate the source from which radiation originates and the amount of radiation. To do this, MCNPX option called cell source was used. In order to perform Monte Carlo simulation, an input statement is written. The number of characters included in the input statement is called word. The reconstructed three-dimensional image contains approximately 1000 ellipses and the number of characters in the MCNPX input sentence for defining one ellipse is about 10-14. Therefore, if you define the position in one cell, you need 10000 ~ 14000 words, but since MCNPX cannot use more than 2000 words in one cell, you need to split the 3D image reconstructed into 5-7 cells. Needs to be. For example, an ellipse from 1 to 200 can write an input statement in cell 1, an ellipse from 201 to 400 cell 2, and an ellipse from ..., 801 to 1000 cell 5 can be written. In other words, there is a limit on the number of characters in one cell, so it is necessary to use multiple cells. This is one of the characteristics of MCNPX and must be kept in mind. In this case, as the cell corresponding to the leg of the object has a low source weight as a whole, a source efficiency low error may occur. Therefore, the cell corresponding to the leg fills up to 2000 words as much as possible. The number of iterations by the Monte Carlo technique was 4 × 10 ⁶ and the energy efficiency was calculated using the F8 evaluation option (Tally) (Los Alamos National Laboratory, Los Alamos, NM) (2000). The number of iterations was set so that the statistical error was less than 5% for each energy band.

Since the coefficient corrector 130 already knows the radioactive intake of the object, the coefficient correction unit 130 may calculate the coefficient efficiency by calculating a ratio of the measured value through the body counter with respect to the radioactive intake of the object. The unit of measurement of the body counter can use 'count', which is a value per unit time. For example, if the amount of radioactive material ingested by the subject is 200 g and the measured value through the body counter is 100 count, the counting efficiency of the subject becomes 0.5 (1/2). In addition, the coefficient correction unit 130 sets the calculated coefficient efficiency as the coefficient efficiency for the corresponding object to perform coefficient efficiency correction.

Thereafter, the dose measuring unit 140 measures the dose of the internal exposure of the object by using the corrected counting efficiency.

Since the object of the present invention is to develop a technique that replaces the current body counting technique, various types of subjects were measured based on the current body counting technique, and compared with the method of manufacturing and measuring a patient-specific mockup proposed by the present invention. saw. In the patient-specific radiation measuring system 100 of the present invention, as a measuring device, a chair type body counter was used. Anthropometry includes a lead-shielded chair, an HPGe meter (CANBERRA Model GC9021), and a collimator with a cone angle of 90 degrees. The position of the main counter can be adjusted but not moved while optimized for standard objects. The counter is located 38cm from the bottom of the chair and 35cm from the bottom of the chair. In order to reduce the chance of measurement error, the measurement time is 1 hour. The measurement data was analyzed by Genie 2000 and the measurement results for the male standard subjects are shown in FIG. 11.

Assuming that the coefficient efficiency value obtained by the family simulation experiment is a true value and the coefficient efficiency calculated by the present invention is approximated to the true value, the results of the family simulation experiment showed that the female and male subjects were hardly different from each other. The experiment was omitted. In all subjects, the relative error from the true value does not exceed 27%, and the statistical error does not exceed 8%.

The 27% error is a large number, but the coefficient efficiency correction method using the reconstructed three-dimensional image does not generate an error due to the physique, and as a result, the potential error when the coefficient efficiency is corrected using only the existing adult standard mockup, It does not generate the error (up to 70% based on the family mock experiment), thereby reducing the error of about 43%. In addition, 27% is the maximum error of each object by energy, and satisfies around 8% on average. Data for calculating the potential error for each energy by the family model and reducing the error using the reconstructed 3D image can be seen in FIGS. 13 and 15. In FIG. 12, it is assumed that a 4 year old child subject needs to be measured. In FIG. 12, since only existing data exist for male subjects, the difference with the 4-year-old subject based on the male subject is represented as a potential error. Therefore, the entire potential error due to the energy of the radionuclide is colored. In the system of the present invention, which can be seen in FIG. 13, the 4 year old measurement is calibrated using a 4 year old reconstructed 3D image, and thus the potential error is calculated based on the 4 year old reconstructed 3D image. You can see that the painted area, the overall potential error, is significantly reduced. Similarly, the case of measuring age 10 can be seen in FIGS. 14 and 15. It can be seen that the error is reduced in FIG. 15 compared to FIG. 14.

While the above methods have been described through specific embodiments, the methods may also be implemented as computer readable code on a computer readable recording medium. Computer-readable recording media include all types of recording devices that store data that can be read by a computer system. Examples of computer-readable recording media include ROM, RAM, CD-ROM, magnetic tape, floppy disks, optical data storage devices, and the like, which are also implemented in the form of carrier waves (for example, transmission over the Internet). Include. The computer readable recording medium can also be distributed over network coupled computer systems so that the computer readable code is stored and executed in a distributed fashion. In addition, functional programs, codes, and code segments for implementing the above embodiments can be easily deduced by programmers of the present invention.

In addition, while the present invention has been described in connection with some embodiments, it is to be understood that various modifications and changes can be made without departing from the spirit and scope of the invention as will be understood by those skilled in the art. You will need to know It is also contemplated that such variations and modifications are within the scope of the claims appended hereto.

1 is a block diagram showing the configuration of a patient-specific radiation measurement system according to an embodiment of the present invention.

Figure 2 is an exemplary view showing the configuration of a patient-specific radiation measurement system according to an embodiment of the present invention.

3 is an exemplary view of a BOMAB object assuming a human body according to an embodiment of the present invention.

Figure 4 is an exemplary view showing an image separated from the background in the optical image according to an embodiment of the present invention.

5 is an exemplary diagram of a program for reconstructing a BOMAB object according to an embodiment of the present invention.

6 is an exemplary view showing a specific cross section of the BOMAB object according to an embodiment of the present invention.

7 is an exemplary view showing a three-dimensional reconstruction image of a BOMAB object according to an embodiment of the present invention.

8 is an exemplary view showing a three-dimensional reconstructed image of the human body according to an embodiment of the present invention.

9 is an exemplary view showing a family BOMAB object and a reconstructed image according to an embodiment of the present invention.

10 is an exemplary view showing a Monte Carlo simulation according to an embodiment of the present invention.

11 is an exemplary view of a comparative measurement experiment using an actual radiation source.

12 is an exemplary view showing an error occurring when measuring the internal exposure of a 4 year old child using the conventional method.

13 is an exemplary view showing an error occurring when measuring the internal exposure of a 4 year old child according to an embodiment of the present invention.

14 is an exemplary view showing an error occurring when measuring the internal exposure of a 10-year-old child using the conventional method.

15 is an exemplary view showing an error occurring when measuring the internal exposure of a 10-year-old child according to an embodiment of the present invention.

Claims (6)

In patient-specific radiation measuring system, A three-dimensional image forming unit configured to form a three-dimensional image based on an optical image of an object of which radiation intake is known; A computer simulation unit for performing computer simulation on the 3D image; A coefficient correction unit for calculating a telegraph counter counting efficiency for the computerized 3D image and performing coefficient correction on the 3D image using the counting efficiency; And Dose measuring unit for measuring the radiation dose to the coefficient-corrected three-dimensional image Patient-specific radiation measurement system comprising a. The method of claim 1, The 3D image forming unit, Taking a front and side optical image of the object to form a two-dimensional array, and the two-dimensional array layered in the axial direction perpendicular to the first axis and the second axis for the two-dimensional array to form a three-dimensional array And forming a lateral rotation array by rotating a three-dimensional array corresponding to the side optical image, and synthesizing the three-dimensional array and the lateral rotation array corresponding to the front optical image to form the three-dimensional image. Customized radiation measurement system. The method of claim 2, The computer simulation unit, A patient-specific radiation measurement system that performs computer simulation by merging a certain number of volumes to improve the speed of simulation. In the patient-specific radiation measurement method, a) forming a three-dimensional image based on an optical image of a subject whose radiation intake is known; b) performing computer simulation on the 3D image; c) calculating a systemic counter counting efficiency for the computerized 3D image; d) performing coefficient correction on the three-dimensional image using the calculated coefficient efficiency; And e) measuring the radiation dose to the coefficient corrected three-dimensional image Patient-specific radiation measurement method comprising a. The method of claim 4, wherein Step a) is Photographing the front and side optical images of the object to form a two-dimensional array; Forming a three-dimensional array by layering the two-dimensional array in the axial direction perpendicular to the first axis and the second axis with respect to the two-dimensional array; Forming a lateral rotation array by rotating a three-dimensional array corresponding to the lateral optical image; And Synthesizing the three-dimensional array corresponding to the front optical image and the side-rotation array to form the three-dimensional image Patient-specific radiation measurement method comprising a. The method of claim 5, Step b), Patient-specific radiation measurement method that performs a computer simulation by merging a predetermined number of volumes to improve the speed of the simulation.

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