KR101823958B1 - Phantom dosimeter and phantom dosimeter system using the same - Google Patents

Abstract

The present invention relates to a phantom radiation dosimeter. The phantom radiation dosimeter includes multiple X-ray sensing probes and a chest phantom modeling the chest of a human body with respect to the X-rays. The chest phantom includes two panels formed to be spaced apart while having a space corresponding to a first gap. A first panel among the two panels, which is arranged on the upper part, includes multiple holes formed on the center part of areas individually divided in the shape of a virtual grid on the upper surface of the first panel. The X-ray sensing probes can be at least partially inserted into the holes from the lower surface of the first panel to the upper surface to have ends exposed on the upper surface of the first panel.

Description

[0001] PHANTOM DOSIMETER AND PHANTOM [0002] DOSIMETER SYSTEM USING THE SAME [0003]

The present invention relates to a phantom radiation dosimeter and a phantom radiation dosimeter system using the same.

The International Commission on Radiological Protection (ICRP) and the International Atomic Energy Agency (IAEA) are working to reduce the amount of dose received by the patient, depending on the type of test, Guidance levels have been established and the establishment and application of diagnostic reference levels (DRL) has been recommended to each country. Therefore, in Korea, we are conducting research on patient dose evaluation to establish DRL in diagnostic radiology field according to domestic situation.

The level of entrance surface dose (ESD), which is the standard for determining the absorbed dose of a patient in most diagnostic radiology fields, including current chest X-ray, has been established, Is underway. However, there is relatively little research on the development of a dosimeter that can precisely measure the patient's real-time dose information and inform the patient of the degree of exposure in advance by an alarm as an auxiliary medical device of the diagnostic radiographic imaging system.

On the other hand, there are a calculation method, an indirect measurement and a direct measurement in order to measure a patient's ESD according to the X-ray irradiation in the diagnostic radiography area.

First, the calculation method is an ESD calculation method in which the NDD-M (non-dosimeter dosimetrymodify) method is first attempted. It has an advantage that ESD can be easily obtained by using the hardware specification of the X-ray imaging system. However, Rigorous hardware management of X-ray generators, including X-ray tubes and generators, is required. Therefore, a new calculation formula that can estimate the ESD value accurately is being studied by domestic and overseas research team.

Secondly, the indirect measurement method is a dosimeter in which a DAP meter is used to measure a dose area product (DAP). The dose is measured without interfering with the X-ray imaging process without leaving traces on the image Can be effective equipment. However, the indirect measurement method using the DAP meter has a disadvantage that the accurate field size and the backscatter factor (BSF) are required when changing the DAP value (mGy · cm ² ) to the ESD value (mGy) through the equation.

Finally, the direct measurement method is the most commonly used ESD measurement method, such as a thermoluminescence dosimeter (TLD), a glass dosimeter, an ionization chamber, and a semiconductor detector.

However, in case of TLD or glass dosimeter, since it requires reading process using special equipment after measurement, it is impossible to measure the dose in real time and it takes long time to read. The ionization ionizer has a large volume of sensing part, And is sensitive to pressure, a calibration process is indispensable. In the case of the semiconductor dosimeter, since it is made of a material having a high atomic number, it is overresponses due to the photoelectric effect in the irradiation of the low energy X-ray beam used in the diagnosis area, and the leakage current is large There are disadvantages.

In order to overcome the disadvantages of the above-mentioned dosimeter and measurement method, it is necessary to prevent unnecessary exposure of the patient and to transmit the dose delivered to the patient to the patient in real time in a control room located at a remote place rather than the examination room It must be able to measure quickly and accurately.

Therefore, it is necessary to research and develop a new type of radiation dosimeter that combines the advantages of direct measurement method and indirect measurement method.

The background technology of the present application is disclosed in Korean Patent Registration No. 10-1214538 (registered on December 14, 2012).

The present invention has been made to solve the above-mentioned problems of the prior art, and it is an object of the present invention to provide an X-ray diagnostic apparatus and a X-ray diagnostic apparatus which can reduce unnecessary coverage of a patient by observing a diagnostic reference level (DRL) The present invention aims to provide a phantom radiation dosimeter capable of promptly executing a quality assurance (QA) program for grasping the quality of a beam and a phantom radiation dosimeter system using the same.

SUMMARY OF THE INVENTION It is an object of the present invention to provide a phantom radiation dosimeter capable of quickly and accurately measuring a two-dimensional plane dose distribution by one beam irradiation and a phantom radiation dosimeter system using the same.

The present invention is directed to solve the above-described problems of the prior art, and it is an object of the present invention to provide an ESD value at a center of a beam irradiation field, which is a reference for determining a patient's absorbed dose in a diagnostic radiation, And to provide a phantom radiation dosimeter system using the same.

The present invention has been made to solve the above problems of the prior art, and it is an object of the present invention to provide a phantom device capable of measuring a two-dimensional surface dose distribution at one time by a single beam irradiation and converting all absorbed dose measured at a non- A radiation dose meter and a phantom radiation dosimeter system using the same.

It is to be understood, however, that the technical scope of the embodiments of the present invention is not limited to the above-described technical problems, and other technical problems may exist.

As a technical means for achieving the above technical object, a phantom radiation dosimeter according to an embodiment of the present invention includes a plurality of X-ray detection probes and a chest phantom modeling a chest of a human body with respect to X-rays, Wherein the chest phantom includes two panels spaced apart with a space corresponding to a first gap, and a first panel located at an upper one of the two panels is disposed on an upper surface of the first panel Ray detection probes so that one end of each of the plurality of X-ray detection probes is exposed on an upper surface of the first panel, and a plurality of X- A probe may be inserted into at least a portion of the plurality of holes from the lower surface of the first panel toward the upper surface.

The X-ray detection probe includes a plastic optical fiber and a plastic optical fiber. The plurality of X-ray detection probes are inserted into the plurality of holes so that one end of the plastic optical fiber is exposed on the upper surface of the first panel. .

In addition, the plurality of X-ray detection probes may be square.

One end of the plurality of exposed X-ray detection probes may be located on the same plane as the upper surface of the first panel.

In addition, the two panels of the chest phantom may each include a laminated PMMA (polymethyl methacrylate) block and an aluminum panel interposed between the PMMA blocks.

The number of holes may be 25.

The plurality of X-ray detection probes may be inserted into a plurality of holes of the first panel at regular intervals.

Further, a hole of the plurality of holes, in which the X-ray detection probe is not received, may be blocked.

Meanwhile, the phantom radiation dosimeter system according to one embodiment of the present invention includes a phantom radiation dosimeter according to one embodiment of the present invention, a transmission optical fiber for transmitting a scintillation signal generated through the phantom radiation dosimeter, An image intensifier, and a camera for outputting a scintillation image based on the amplified scintillation signal.

In addition, the phantom radiation dosimeter system according to an embodiment of the present invention may further include a connector for connecting the plastic optical fiber and the transmission optical fiber.

Meanwhile, in the method of measuring a radiation dose according to one embodiment of the present invention, the radiation dose can be measured using the phantom radiation dosimeter according to one embodiment of the present invention.

The above-described task solution is merely exemplary and should not be construed as limiting the present disclosure. In addition to the exemplary embodiments described above, there may be additional embodiments in the drawings and the detailed description of the invention.

According to the above-mentioned problem solving means of the present invention, by providing a sensing panel provided with a two-dimensional array of sensing probes by inserting a plurality of X-ray sensing probes into holes formed in regions divided into grids, Dimensional plane dose distribution can be measured at a time and the entrance surface dose (ESD), which is a reference for determining the absorbed dose of the patient, can be measured quickly and accurately.

According to the present invention, there is provided a phantom radiation dosimeter for measuring a two-dimensional plane dose distribution and a phantom radiation dosimeter system using the same, There is an effect that a quality management program for reducing the coating and grasping the quality of the X-ray beam can be performed quickly.

According to the above-mentioned problem solving means, it is possible to provide a phantom radiation dosimeter capable of measuring a two-dimensional plane dose distribution with a single beam irradiation and a phantom radiation dosimeter system using the same, absorbed dose to ESD and simultaneous measurement of dose at each measurement point in the beam irradiation field.

According to the above-described task solution of the present invention, based on a modified direct dosimetry, which combines the advantages of a direct measurement method capable of accurately measuring a radiation dose and an indirect measurement method not affecting a radiation image By providing a phantom radiation dosimeter and a phantom radiation dosimeter system using the same, it is possible to solve the disadvantages of short channel (single channel) measurement of conventional radiation dosimeters, generation of artifacts in radiographic images, and obstruction of diagnostic tests .

According to the above-mentioned problem solving means of the present invention, by using a phantom radiation dosimeter having a plurality of X-ray detecting probes, the area corresponding to the center of the irradiation field of the X-ray beam and the area corresponding to the edge, By measuring the generated glare signals at the same time and acquiring a relation between the center of the field and the edge, the absorbed dose value measured at the edge is converted into the ESD value at the center by using the corrected direct dose measurement, It is possible to measure the ESD value at the center of the field of study, which serves as a reference for determining the absorbed dose of the patient in the diagnostic radiation, in real time.

FIG. 1 is a schematic view of a phantom radiation dosimeter according to an embodiment of the present invention. Referring to FIG.
2A is a schematic view illustrating the structure of an x-ray detection probe included in a phantom radiation dosimeter according to an embodiment of the present invention.
FIG. 2B is a view schematically showing another structure of an x-ray detection probe included in a phantom radiation dosimeter according to an embodiment of the present invention.
3 is a schematic view showing the structure of a chest phantom included in a phantom radiation dosimeter according to an embodiment of the present invention.
FIG. 4 is a view illustrating an example in which an x-ray detection probe is arranged in a phantom radiation dosimeter according to an embodiment of the present invention.
5 is a view showing another example in which an x-ray detection probe is arranged in a phantom radiation dosimeter according to an embodiment of the present invention.
FIG. 6 is a diagram illustrating an example of an experiment configuration using a DR system as a diagnostic radiator to evaluate the performance of a phantom radiation dosimeter system including a phantom radiation dosimeter according to an embodiment of the present invention.

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings so that those skilled in the art can easily carry out the present invention. It should be understood, however, that the present invention may be embodied in many different forms and should not be construed as limited to the embodiments set forth herein. In the drawings, the same reference numbers are used throughout the specification to refer to the same or like parts.

Throughout this specification, when an element is referred to as being "connected" to another element, it is intended to be understood that it is not only "directly connected" but also "electrically connected" or "indirectly connected" "Is included.

It will be appreciated that throughout the specification it will be understood that when a member is located on another member "top", "top", "under", "bottom" But also the case where there is another member between the two members as well as the case where they are in contact with each other.

Throughout this specification, when an element is referred to as "including " an element, it is understood that the element may include other elements as well, without departing from the other elements unless specifically stated otherwise.

In the entire specification, the numerical values and the numbers specifically described are merely examples, but are not limited thereto.

In this paper, we propose a phantom dose measurement system that can measure the 2D surface dose distribution with one beam irradiation and the entrance surface dose (ESD) And a phantom radiation dosimeter system using the same.

FIG. 1 is a view schematically showing a configuration of a phantom radiation dosimeter according to an embodiment of the present invention, and FIG. 2 is a view schematically showing the structure of an X-ray detection probe included in a phantom radiation dosimeter according to an embodiment of the present invention And FIG. 3 is a schematic view showing the structure of a chest phantom included in the phantom radiation dosimeter according to one embodiment of the present invention.

1, a phantom radiation dosimeter 100 according to an embodiment of the present invention includes a plurality of x-ray detection probes 10 and a chest phantom 20 modeling the human chest region with respect to x-rays. . The structure of the x-ray detection probe 10 and the structure of the chest phantom 20 can be more easily understood with reference to Figs. 2A and 3.

2A, an x-ray sensing probe 10 included in a phantom radiation dosimeter 100 according to an embodiment of the present invention includes a plastic scintillating fiber (PSF) 11 and a plastic optical fiber , POF) 12, as shown in FIG.

The plastic scintillation optical fiber 11 can be, for example, an optical fiber composed of an organic scintillator. More specifically, the atomic number of the constituents of the organic scintillator is generally 10 or less, the density is low, and the main interaction is Compton scattering. A plastic scintillation optical fiber 11 composed of an organic scintillator is characterized in that fluorescent dopants are added to a core portion of a plastic optical fiber 12 for transmitting an optical signal and react with radiation to generate light in a visible light region I have. Also, since the optical fiber is composed of the same core / cladding structure as that of the optical fiber, it has an advantage that the optical characteristic is excellent and the transmission of the scintillating signal is advantageous.

Therefore, in one embodiment of the present invention, a BCF series (Saint-Gobain Ceramic & Plastics), which is an organic scintillator, may be used as a sensing material of the x-ray sensing probe 10. Particularly, the scintillation optical fiber can be divided into BCF-10, 12, 20 and 60 according to the characteristics of the scintillating material added to the core portion, and the scintillation efficiency is improved according to the radiation source, energy, BCF-12, which has the highest scintillation efficiency among the four types of scintillation optical fibers (BCF-10, 12, 20, 60), can be used as a sensing material in this embodiment .

Meanwhile, the plastic optical fiber 12 may be replaced with a glass optical fiber, and may be divided into a square optical fiber and a round optical fiber according to the shape. Also, according to the refractive index distribution of the core, it can be classified into a graded-index optical fiber and a step-index optical fiber. In the case of the hill type refractive index optical fiber, the distortion of the transmitted optical signal can be minimized. However, since the diameter of the stepped refractive index optical fiber is larger than the diameter of the commercially available hill type refractive index optical fiber, a stepped refractive index optical fiber is advantageous in view of the amount of transmitted light.

For example, GH-4001 (Mitsubishi Rayon), which is a multimode optical fiber having a hill type refractive index, may be used as the plastic optical fiber 12 for transmission of a weak flash signal in one embodiment of the present invention. According to an embodiment of the present invention, the core portion of the plastic optical fiber 12 may be made of polymethylmethacrylate (PMMA) having a refractive index of 1.49 and the cladding may be formed of a fluorinated polymer having a refractive index of 1.402. , NA) may be 0.5. Further, the diameter of the core may be 0.98 mm, and the outer diameter of the optical fiber may be 1 mm.

An example of a manufacturing process of the x-ray sensing probe 10 used in the present invention will be described with reference to FIG. 2A. In order to minimize the connecting loss and attenuation and to increase the light transmission efficiency, the plastic optical fiber 11 and the plastic optical fiber 12 ) Can be polished by using various kinds of lapping films. In order to reduce light loss due to Fresnel's reflection between the scintillator of the plastic scintillation optical fiber 11 and the plastic optical fiber 12 when the polished plastic scintillation optical fiber 11 and the plastic optical fiber 12 are connected, An optical epoxy 13 may be applied between the plastic optical fiber 11 having a length of 10 mm and the plastic optical fiber 12 having a length of 6 m.

The plastic scintillation optical fiber 11 is arranged so that the scintillation signal generated by the interaction with the low energy X-rays in the plastic scintillation optical fiber 11 is transmitted to the optical metrology equipment through the plastic optical fiber 12 without loss to the outside. A Teflon reflective tape 14 may be coated on the outer surface of the substrate. The outer side of the plastic optical fiber 11 and the plastic optical fiber 12, that is, the outside of the sensing probe 10, is made of polyethylene (PE) to prevent the influence of light noise due to visible light from the outside. And a black jacket 15 having an outer diameter of 2.5 mm.

In FIG. 2A, the x-ray detection probe 10 according to one embodiment of the present invention may have a plastic optical fiber 11 and a plastic optical fiber 12 in a circular shape. However, the shape of the optical fiber is not limited thereto, and may be square as shown in FIG. 2B.

FIG. 2B is a view schematically showing another structure of an x-ray detection probe included in a phantom radiation dosimeter according to an embodiment of the present invention.

Referring to FIG. 2B, the x-ray sensing probe 10 'according to another embodiment of the present invention may include a square plastic optical fiber 11 and a square plastic optical fiber 12. The phantom radiation dosimeter of the present invention is configured such that when the x-ray detection probe 10 'is inserted into the chest phantom 20, the first optical fiber 11 and the optical fiber 12 are formed in a square shape, It is possible to effectively reduce a dose measurement error that may occur in a gap between the X-ray detecting probe 20a and the X-ray detecting probe 10 '.

The plastic optical fiber 11 and the outside of the plastic optical fiber 12 are arranged so that the flash signal generated by the interaction with the low energy X-ray inside the flash optical fiber 11 can be transferred to the optical measuring equipment without loss to the outside. A reflective paint 14 may be applied. In addition, a portion of the plastic optical fiber 12 may be coated with black tape.

An x-ray sensing probe 10 'including a plastic flash optical fiber 11 and a plastic optical fiber 12 can be inserted into the first panel 20a of the chest phantom 20 (see, for example, 11) and the end portion of the plastic optical fiber 12). The lower portion of the sensing probe 10 'inserted into the chest phantom 20 is connected to the lower portion of the sensing probe 10' through a connector 17 to transmit a scintillation signal generated from the sensing probe 10 ' And may be connected to a transmitting optical fiber (TOF) 16 of a round type. The transmission optical fiber 16 may be wrapped with a black jacket 15 to prevent the influence of light noise due to external visible light. According to one embodiment of the present invention, the plastic optical fiber 11 and the plastic optical fiber 12 may be square, and the transmission optical fiber 16 may be round. Since the plastic scintillation optical fiber 11 and the plastic optical fiber 12 which are the regions to be inserted into the chest phantom 20 are square, the distance between the first panel 20a of the chest phantom 20 and the x- It is possible to effectively reduce the dose measurement error that may occur in the gap.

The transmission optical fiber 16 and the X-ray sensing probe 10 may be integrally formed as shown in FIG. 2A (the transmission optical fiber 16 and the plastic optical fiber 12 are integrally connected) The transmission optical fiber 16 and the X-ray sensing probe 10 'may be connected through the connector 17 as well. In the following description, the transmission optical fiber 16 and the x-ray sensing probe 10 are integrated and will be described by way of example.

3, the chest phantom 20 included in the phantom radiation dosimeter 100 according to one embodiment of the present invention includes two panels 20a and 20b spaced apart from each other by a space corresponding to the first space d, 20b.

According to one embodiment of the invention, the two panels 20a, 20b may each comprise a laminated PMMA (polymethyl methacrylate) block and an aluminum panel interposed between the PMMA blocks. More specifically, the first panel 20a located at the upper one of the two panels 20a and 20b is inserted between the two PMMA blocks 21a and 23a stacked and the two PMMA blocks 21a and 23a stacked And an aluminum panel 22a. The second panel 20b positioned below the two panels 20a and 20b is formed by stacking the two PMMA blocks 21b and 23b and the aluminum panel inserted between the two PMMA blocks 21b and 23b 22b.

The two panels 20a, 20b of the chest phantom 20 are modeled as human bodies and can have nearly water-equivalence properties. Also, according to one embodiment of the present disclosure, the two panels 20a, 20b of the chest phantom 20 may include a solid water phantom.

The chest phantom 20 may also include a plurality of supports 40 that support between two panels 20a and 20b spaced apart by a first spacing d, .

The phantom radiation dosimeter 100 of the present application is configured to arrange a plurality of x-ray detection probes 10 two-dimensionally on the chest phantom 20 in order to quickly and accurately measure the two-dimensional plane dose distribution through one beam irradiation .

To this end, the first panel 20a located at the upper one of the two panels 20a and 20b is provided with a plurality of holes 30 (see FIG. 1) formed at the center of each of the regions divided by the grid with respect to the upper surface of the first panel 20a ). An x-ray sensing probe 10 may be inserted into at least some of the holes of the plurality of holes 30. The plurality of x-ray detection probes 10 are arranged such that one end of the plurality of x-ray detection probes 10 is exposed from the lower surface of the first panel 20a to the upper surface of the first panel 20a, And can be inserted into at least a part of the holes of the plurality of holes 30 toward the center. One end of the plurality of x-ray detection probes 10 exposed on the upper surface of the first panel 20a may be one end of the plastic optical fiber 11 included in the x-ray detection probe 10. That is, when the plurality of x-ray detection probes 10 are inserted into the plurality of holes 30, the first panel 20a is formed so that one end of the plastic optical fiber 11 is exposed on the top surface of the first panel 20a, To the upper surface.

One end of the plurality of x-ray detection probes 10 exposed on the upper surface of the first panel 20a may be located on the same plane as the upper surface of the first panel 20a.

Although a plurality of x-ray detection probes 10 and a plurality of holes 30 are illustrated as being round in the description of the present invention, a plurality of x-ray detection probes 10 and The plurality of holes 30 may be formed in a square.

The first panel 20a having a plurality of x-ray detection probes 10 may be referred to as a two-dimensional sensing panel.

An example in which a plurality of x-ray detection probes 10 are two-dimensionally arranged can be more easily understood with reference to Figs. 4 and 5. Fig.

FIG. 4 is a plan sectional view of the first panel 20a showing an example in which the x-ray detection probes are two-dimensionally arranged in the phantom radiation dosimeter according to the embodiment of the present invention.

Referring to FIG. 4, for example, nine holes 30 may be formed in the central portion of each of the regions divided into the virtual 3 x 3 grid 1 in the first panel 20a, Each of the X-ray detection probes 10 can be inserted. At this time, with respect to each of the nine x-ray detection probes 10, the scintillation signal generated by the interaction with the x-ray beam inside the scintillation optical fiber 11 included in the X- Can be transmitted to the image intensifier tube to be described later through the plastic optical fiber 12 (and the optical fiber for transmission) located below the optical fiber 11.

5 shows another example in which the x-ray detection probes are arranged two-dimensionally in the phantom radiation dosimeter according to one embodiment of the present application, and shows a top cross-sectional view of the first panel 20a.

5 (a) shows a plurality of holes formed in the first panel 20a, FIG. 5 (b) shows an example in which nine X-ray sensing probes 10 are arranged in two dimensions, Shows an example in which nine x-ray detection probes 10 are arranged in two dimensions different from Fig. 5 (b).

Referring to FIG. 5 (a), for example, the first panel 20a may have 25 holes 30 at the center of each of the regions divided into virtual 5 × 5 grids 1.

A plurality of x-ray detection probes (10) can be inserted into some holes of the plurality of holes (30). For example, when a plurality of x-ray detection probes 10 are inserted into nine holes of the 25 plurality of holes 30, the plurality of x-ray detection probes 10 may be formed as shown in Fig. 5 (b) or 5 As shown in FIG.

5 (b) to 5 (c), a plurality of x-ray detection probes 10 are inserted into holes 31 of a plurality of holes 30 of the first panel 20a at equal intervals Whereby a plurality of x-ray detection probes 10 can be arranged in two dimensions. In addition, the hole 32 in which the x-ray detection probe 10 is not received among the plurality of holes 30 may be clogged. the accuracy of x-ray dose measurement can be improved by blocking the hole 32 in which the x-ray detection probe 10 is not inserted. In describing the present invention, the number of the plurality of holes 30, the number of the plurality of x-ray detection probes 10, and the like are merely one embodiment, but are not limited thereto. it is desirable to insert as many x-ray detection probes 10 as possible in order to increase the accuracy and promptness of x-ray dose measurement.

The present invention provides a phantom radiation dosimeter 100 capable of measuring a two-dimensional plane dose distribution with a single beam irradiation, and a phantom radiation dosimeter system using the same, thereby reducing all absorbed doses measured at a portion other than the center to ESD And simultaneous measurement of the dose at each measurement point in the beam irradiation field is possible.

Hereinafter, the configuration of the phantom radiation dosimeter system including the phantom radiation dosimeter according to one embodiment of the present invention will be briefly described based on the details described above.

FIG. 6 is a flow chart illustrating a method for evaluating the performance of a phantom radiation dosimeter system 700 including a phantom radiation dosimeter 100 according to one embodiment of the present invention, for example, a digital radiography system 600 (radiographic imaging system) (DR) system using a digital radiography (DR) system. FIG. 6 is a graph showing the relationship between the ESD (entrance surface dose) at the center and the absorbed dose at the periphery by measuring the 2D surface dose distribution, and FIG. Of the phantom radiation dosimeter 100 shown in FIG.

Referring to FIG. 6, the diagnostic radiological apparatus 600 is a medical apparatus for applying the phantom radiation dosimeter 100 according to an embodiment of the present invention, and may be referred to as a radiographic imaging system. 601, an X-ray tube, a collimator 602, and an image receptor 603. The diagnostic radiology apparatus 600 can acquire an anatomical image of the human body by irradiating X-rays.

6, in order to evaluate the performance of a phantom dosimeter system 700 comprising a phantom dosimeter 100 and a light-measuring device according to an embodiment of the present invention , And a DR system (diagnostic radiology apparatus 600). As a result of this experiment, the phantom radiation dosimeter 100 according to one embodiment of the present invention is an auxiliary medical instrument of the diagnostic radiological apparatus 600 (radiographic image system) and can be used for real time dose measurement. And the like.

In radiographic imaging using the radiographic imaging system 600 as a diagnostic radiator, a phantom radiation dosimeter system 700 according to an embodiment of the present invention includes a plurality of x-ray detection probes 10 in the chest phantom 20 A transferring optical fiber 12 for transferring a scintillation signal generated from the scintillation optical fiber 11 of the x-ray sensing probe 10 in the phantom radiation dosimeter 100, a transmission optical fiber A CMOS camera module 704 (CMOS) for measuring a scintillation signal amplified by an image intensifier 703 and an image intensifier 703 for amplifying a scintillation signal transmitted from the display device 12 and outputting a scintillation image to a display device, camera module). In addition, the phantom radiation dosimeter system 700 according to one embodiment of the present invention includes a coherent bundle 701 and a plastic holder 702 supporting a plurality of transmission optical fibers 12, an image intensifier 703, An optical rail 705 and a light-tight box 706 for supporting and receiving the light source 704. The phantom radiation dosimeter system 700 according to one embodiment of the present invention can reduce the unnecessary coverage of the patient by observing a diagnostic reference level (DRL), and determine the beam quality of the X-ray beam Quality assurance (QA) programs can be performed quickly.

Here, the structure of the phantom radiation dosimeter 100 has been described in detail in the foregoing description and will not be described below. In the example of FIG. 6, there may be nine X-ray sensing probes 10, so that the phantom radiation dosimeter system 700 including the phantom radiation dosimeter 100 according to one embodiment of the present invention uses nine channels and can be connected to the x-ray detection probe 10.

6, the transmitting optical fiber 12 is integrated with the plastic optical fiber 12 of the x-ray detecting probe 10, but the present invention is not limited to this, The plastic optical fiber of the line-sensing probe 10 may have a separate structure as shown in FIG. 2B. In this case, the phantom radiation dosimeter system 700 according to an embodiment of the present invention may include a connector 17 connecting the plastic optical fiber included in the x-ray detection probe 10 and the transmission optical fiber.

Specifically, when the X-ray beam is irradiated in the radiation imaging system 600, nine scintillation signals are generated in the two-dimensional sensing panel 20a located at the upper end of the chest phantom 20, and through the transmission optical fiber 12 The transmitted weak scintillation signal can be measured in real time through the CMOS camera module 704 after the intensity of the light is amplified through the image intensifier 703.

The real-time scintillation image (RSI) output from the CMOS camera module 704 is converted into an RGB (red-green-blue) image file by MATLAB (MathWorks) . ≪ / RTI > At this time, in order to calibrate each x-ray sensing probe 10 to the same state, the changed image file can be multiplied by the calibration factor obtained before the experiment, By summing the gray scale values, the light intensity and distribution of the scintillation signal generated in each channel can be obtained.

Meanwhile, the radiation dose measurement method according to one embodiment of the present invention can be performed by the phantom radiation dosimeter 100 described above and the phantom radiation dosimeter system 700 using the same. Therefore, in the radiation dose measurement method described above, the same contents as those of the phantom radiation dosimeter 100 and the phantom radiation dosimeter system 700 can be applied in the same manner.

In this embodiment, the phantom radiation dosimeter 100 having a plurality of X-ray detection probes is used to simultaneously measure each of the scintillation signals generated in accordance with the interaction with the X-ray at the center and the edge of the irradiation field of the X- By acquiring the relationship between the center and the edge and then converting the absorbed dose measured at the edge to the ESD value at the center using the modified direct dose measurement method, The ESD value at the center of the irradiation field as a reference for determining the absorbed dose can be easily measured in real time.

The radiation dose measurement method according to one embodiment of the present invention may be implemented in the form of a program command that can be executed through various computer means and recorded in a computer readable medium. The computer-readable medium may include program instructions, data files, data structures, and the like, alone or in combination. The program instructions recorded on the medium may be those specially designed and constructed for the present invention or may be available to those skilled in the art of computer software. Examples of computer-readable media include magnetic media such as hard disks, floppy disks, and magnetic tape; optical media such as CD-ROMs and DVDs; magnetic media such as floppy disks; Magneto-optical media, and hardware devices specifically configured to store and execute program instructions such as ROM, RAM, flash memory, and the like. Examples of program instructions include machine language code such as those produced by a compiler, as well as high-level language code that can be executed by a computer using an interpreter or the like. The hardware devices described above may be configured to operate as one or more software modules to perform the operations of the present invention, and vice versa.

It will be understood by those of ordinary skill in the art that the foregoing description of the embodiments is for illustrative purposes and that those skilled in the art can easily modify the invention without departing from the spirit or essential characteristics thereof. It is therefore to be understood that the above-described embodiments are illustrative in all aspects and not restrictive. For example, each component described as a single entity may be distributed and implemented, and components described as being distributed may also be implemented in a combined form.

The scope of the present invention is defined by the appended claims rather than the detailed description, and all changes or modifications derived from the meaning and scope of the claims and their equivalents should be construed as being included within the scope of the present invention.

100: Phantom radiation dosimeter
10: x-ray detection probe
20: Chest Phantom

Claims (11)

A plurality of X-ray detection probes including plastic optical fibers and plastic optical fibers;
An optical fiber for transmission transmitting a scintillation signal generated from the X-ray detection probe and being integrated with the plastic optical fiber or connected to the plastic optical fiber; And
A chest phantom modeled on a human's chest region with respect to X-rays,
The chest phantom,
And two panels spaced apart from each other with a space corresponding to the first interval,
Wherein a first panel located at an upper portion of the two panels includes a plurality of holes formed in a central portion of each of regions divided into imaginary lattices with respect to an upper surface of the first panel,
The plurality of X-ray detection probes are inserted into at least a part of the plurality of holes from the lower surface of the first panel toward the upper surface so that one end of the plurality of X-ray detection probes is exposed on the upper surface of the first panel Lt; / RTI &
Wherein each of the plurality of X-ray detection probes is configured such that one end of the plastic optical fiber for generating light in a visible light region when exposed to radiation is exposed on an upper surface of the first panel, Is inserted through each of the plurality of holes of the first panel so as to be positioned below the first panel,
Wherein a hole of the plurality of holes in which the X-ray detection probe is not received is closed,
The X-ray detection probe is inserted into the hole of the first panel to reduce a dose measurement error that may occur in a gap between the inner surface of the hole and the outer surface of the X-ray detection probe,
A plurality of X-ray detection probes inserted in a plurality of holes formed in the center of each of the regions divided into virtual lattices on the upper surface of the first panel, and an entrance surface dose (ESD) Wherein the two-dimensional planar distribution of the absorbed dose is measured in real time. delete The method according to claim 1,
Wherein the plurality of X-ray detection probes are square. The method according to claim 1,
Wherein one end of the exposed plurality of X-ray detection probes is coplanar with an upper surface of the first panel. The method according to claim 1,
Wherein the two panels of the chest phantom each comprise a laminated PMMA (polymethyl methacrylate) block and an aluminum panel interposed between the PMMA blocks. The method according to claim 1,
Wherein said plurality of holes are twenty-five. The method according to claim 1,
Wherein the plurality of X-ray detection probes are inserted into a plurality of holes of the first panel at regular intervals. delete 8. A phantom radiation dosimeter according to any one of claims 1, 3, and 7 to 7;
An image intensifier tube for amplifying the scintillation signal; And
A camera for outputting a scintillation image based on the amplified scintillation signal,
And a phantom radiation dosimeter. 10. The method of claim 9,
Further comprising a connector connecting the plastic optical fiber and the transmission optical fiber. delete

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