1
Monte Carlo simulations of production of collimated panoramic X-rays using a conical anode-type X-ray tube Andrii Sofiienko 1 , Chad Jarvis 2 , Ådne Voll 3 1 University of Bergen, Allegaten 55, PO Box 7803, 5020 Bergen, Norway, e-mail: [email protected] 2 Christian Michelsen Research AS, Fantoftveien 38, PO Box 6031, NO-5892 Bergen, Norway, e-mail: [email protected] 3 Visuray AS, Strandbakken 10, 4070 Randaberg, Norway, e-mail: [email protected] Introduction X-ray techniques are commonly used in the non-destructive testing [1] of industrial parts, material characterization and many medical applications [2, 3, 4]. X-ray tubes with a conical target [5, 6] have the simplest design for 360 0 panoramic scanning systems [7]. For scanning technology, maximising the output X-ray intensity in the collimated beam is important. Variations in the electron beam diameter, the shape of the conical target, and the inclination angle of the output collimated X-ray beam can significantly affect the output X-ray intensity in the collimated beam and limit the performance of the scanning system. The general purpose of this study was to investigate, using Monte Carlo simulations, the X-ray generation process in an X-ray tube with a conical tungsten anode and cylindrical symmetry. We determined the following parameters for use in practical applications: the intensity of generated X-rays in the energy range of 250-500 keV, the optimal target shape, the angular distribution of the intensity of the generated X-rays and collimated through a cylindrical hole from an external collimator, and the efficiency of X-ray generation. Monte Carlo simulations The Monte Carlo (MC) simulations were generated with the software suite Xenos by Field Precision [8]. The particular program to generate the Monte Carlo is called GamBet based on the package PPENELOPE [9]. The solution volume for the object mesh had different ranges for the different sizes of the tungsten conical anode (it depends on the apex angle of the conical anode 2γ, Figure 1) and for the different radii of the electron beam (r e ). MC simulations were done for the geometries presented in Figure 1, when the electron energy was 250 keV, 300 keV and 500 keV. The number of high-energy electrons was the same for all simulations: N e = 4.61310 5 . The radial distribution of electrons in an electron beam was modelled as a Gaussian function of the diameter (D e ) of the electron beam: Figure 1: A geometrical model of the conical tungsten target and electron beam that were used for the MC simulations and for the numerical calculation of the intensity of collimated X-rays. The angular distribution of the photon intensity in collimated X-ray beam 2 2 2 2 1 , , exp 2 2 4 4 e e e e x y f xyD D D Figure 3: The dependences of the inclination angle, associated with the maximum value of the intensity of collimated X-rays (upper plot), and of the maximum value of the intensity of collimated X-rays (lower plot) on the value of the apex angle of the conical anode at an electron energy equal to 250 keV and electron beam radii equal to 0.5 mm (1), 2.0 mm (2) and 5.0 mm (3). Figure 4: The dependences of the inclination angle, associated with the maximal value of the intensity of collimated X-rays (upper plot), and of the maximal value of the intensity of collimated X-rays (lower plot) on the value of the apex angle of the conical anode at an electron energy equal to 500 keV and electron beam radii equal to 0.5 mm (1), 2.0 mm (2) and 5.0 mm (3). To simplify the MC simulations, which require a large amount of computation time, the following simple numerical method was used to simulate an external cylindrical collimator with any thickness ∆R and any radius. For this task, it is necessary to know the spatial distribution of the photons on the first surface of the collimator (with inner radius R c ) and on the second surface of the collimator (with outer radius R c + ∆R). This spatial distribution can be calculated using two translations of the spatial positions of the photons on the surface with radius R c and then to the surface with new radius R c + ∆R; moreover, it is necessary to estimate the geometrical position of the cylindrical hole inside the collimator. Only photons whose coordinates lie on the hole on the first collimator surface and on the hole on the second collimator surface will be able to pass through the collimator hole. The parameters of the collimator are following: R c = 10 mm, ∆R = 3.5 mm and r c = 0.45 mm. Conclusions From Monte Carlo simulations of the X-ray generation process in an X-ray tube with a conical target (anode), several important parameters and dependences were determined: the X-ray spectra in the acceleration potential range of 250-500 kV, the optimal target shape, the angular distribution of the intensity of X-rays collimated through the cylindrical hole or slit of an external collimator and the efficiency coefficient for energy transfer from an electron beam to a generated X-ray flux. It was demonstrated that the angular distribution of the intensity in a collimated X-ray beam depends on the radius of the electron beam and on the shape of the conical target and that these dependences are different at different acceleration potentials of the X-ray tube. The optimal values of the geometrical parameters of a scanning system based on an X-ray tube integrated with an external collimator were observed to maximise the output X-ray intensity in the beam. These results and the proposed methods for the numerical modeling of the external collimators can be used in practical applications to design scanning systems based on the pencil-beam technique and X-ray tubes with massive conical targets. References [1] G. Harding, J. Kosanetzky, Scattered X-ray beam nondestructive testing, NIM: Section A, 280, (1989), 517-528. [2] D.N. Zeiger, J. Sun, G.E. Schumacher, S.L. Gibson, Evaluation of dental composite shrinkage and leakage in extracted teeth using X-ray microcomputed tomography, Dental Materials, 25, (2009), 1213-1220. [3] L. Goldstein, S.O. Prasher, S. Ghoshal, Three-dimensional visualization and quantification of non-aqueous phase liquid volumes in natural porous media using a medical X-ray Computed Tomography scanner, J. of Contaminant Hydrology, 93, (2007), 96-110. [4] M. Lindner, L. Blanquart, P. Fischer, H. Krüger, N. Wermes, Medical X-ray imaging with energy windowing, NIM: Section A, 465, (2001), 229-234. [5] A. Ihsan, S.H. Heo, H.J. Kim, C.M. Kang, S.O. Cho, An optimal design of X-ray target for uniform X-ray emission from an electronic brachytherapy system, NIM: Section B, 269, (2011), 1053-1057. [6] G. Harding, B. Jordan and J. Kosanetzky, A new fluorescent X-ray source for photon scattering investigations, Phys. Med. Biol., 36, No.12 (1991), 1573. [7] S. Henzell, S.S. Dhaliwal, R.I. Price, F. Gill, C. Ventourasa, C. Greena, F.D. Fonseca, M. Holzherr, R. Prince, Comparison of Pencil-Beam and Fan- Beam DXA Systems, Journal of Clinical Densitometry, 6, (2003), 205-210. [8] S. Humphries, Computational Techniques in Xenos - Integrated 3D Software Suite for Electron and X-ray Physics, IEEE 34th International Conference ICOPS 2007, 729, 2007. [9] F. Salvat, J.M. Fernández-Varea, J. Sempau, PENELOPE-2011: A code system for Monte Carlo simulation of electron and photon transport, OECD Nuclear Energy Agency, 369, 2011. [10] J.R. Taylor, An introduction to Error Analysis, University Science Books (1996). [11] S.A. Ivanov, G.A.Shchukin, Rentgenovskie trubki tekhnicheskogo naznacheniya (X-ray Tubes for Technical Purposes), Leningrad: Energoatomizdat, 1989 [in Russian]. [12] H.W. Koch, J.W. Motz, Bremsstrahlung Cross-Section Formulas and Related Data, Rev. Mod. Phys., 31, 920, 1959. [13] K.N. Mukhin, Nuclear physics (translated from Russian), Macdonald & Co., 505, 1970. 0 30 60 90 120 150 180 0 2x10 7 4x10 7 6x10 7 8x10 7 5 0 15 0 30 0 45 0 55 0 X (), photons/s , degrees Figure 2: The angular distributions of the intensity of collimated X-ray photons (recalculated for a collimator with a hole) in cylindrical geometry at different values of the apex angle of the anode when the electron energy is equal to 250 keV and the electron beam radius is equal to 2.0 mm.

Monte Carlo simulations of production of collimated panoramic X-rays using a conical anode-type X-ray tube (Andrii Sofiienko)

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Page 1: Monte Carlo simulations of production of collimated panoramic X-rays using a conical anode-type X-ray tube (Andrii Sofiienko)

Monte Carlo simulations of production of collimated

panoramic X-rays using a conical anode-type X-ray tube

Andrii Sofiienko1, Chad Jarvis

2, Ådne Voll

3

1University of Bergen, Allegaten 55, PO Box 7803, 5020 Bergen, Norway, e-mail: [email protected]

2Christian Michelsen Research AS, Fantoftveien 38, PO Box 6031, NO-5892 Bergen, Norway, e-mail: [email protected]

3Visuray AS, Strandbakken 10, 4070 Randaberg, Norway, e-mail: [email protected]

Introduction

X-ray techniques are commonly used in the non-destructive testing [1] of industrial parts, material

characterization and many medical applications [2, 3, 4]. X-ray tubes with a conical target [5, 6] have

the simplest design for 3600 panoramic scanning systems [7]. For scanning technology, maximising

the output X-ray intensity in the collimated beam is important. Variations in the electron beam

diameter, the shape of the conical target, and the inclination angle of the output collimated X-ray

beam can significantly affect the output X-ray intensity in the collimated beam and limit the

performance of the scanning system. The general purpose of this study was to investigate, using

Monte Carlo simulations, the X-ray generation process in an X-ray tube with a conical tungsten anode

and cylindrical symmetry. We determined the following parameters for use in practical applications:

the intensity of generated X-rays in the energy range of 250-500 keV, the optimal target shape, the

angular distribution of the intensity of the generated X-rays and collimated through a cylindrical hole

from an external collimator, and the efficiency of X-ray generation.

Monte Carlo simulations

The Monte Carlo (MC) simulations were generated with the software suite Xenos by Field

Precision [8]. The particular program to generate the Monte Carlo is called GamBet based on the

package PPENELOPE [9]. The solution volume for the object mesh had different ranges for the different sizes of the tungsten conical anode (it depends on the apex angle of the conical anode 2γ, Figure 1) and for the different radii of the electron beam (re). MC simulations were

done for the geometries presented in Figure 1, when the electron energy was 250 keV, 300 keV and

500 keV. The number of high-energy electrons was the same for all simulations: Ne = 4.613∙105.

The radial distribution of electrons in an electron beam was modelled as a Gaussian function of the

diameter (De) of the electron beam:

Figure 1: A geometrical model of the conical tungsten target and electron beam that were used for the MC simulations and for the numerical calculation of the intensity of

collimated X-rays.

The angular distribution of the photon intensity in collimated X-ray beam

2 2

2 2

1, , exp

2 24 4

e e

e e

x yf x y D

D D

Figure 3: The dependences of the inclination angle, associated with the maximum value of the

intensity of collimated X-rays (upper plot), and of the maximum value of the intensity of

collimated X-rays (lower plot) on the value of the apex angle of the conical anode at an

electron energy equal to 250 keV and electron beam radii equal to 0.5 mm (1), 2.0 mm (2) and

5.0 mm (3).

Figure 4: The dependences of the inclination angle, associated with the maximal value of the

intensity of collimated X-rays (upper plot), and of the maximal value of the intensity of

collimated X-rays (lower plot) on the value of the apex angle of the conical anode at an

electron energy equal to 500 keV and electron beam radii equal to 0.5 mm (1), 2.0 mm (2) and

5.0 mm (3).

To simplify the MC simulations, which require a large

amount of computation time, the following simple

numerical method was used to simulate an external

cylindrical collimator with any thickness ∆R and any

radius. For this task, it is necessary to know the spatial

distribution of the photons on the first surface of the

collimator (with inner radius Rc) and on the second

surface of the collimator (with outer radius Rc + ∆R).

This spatial distribution can be calculated using two

translations of the spatial positions of the photons on

the surface with radius Rc and then to the surface with

new radius Rc + ∆R; moreover, it is necessary to

estimate the geometrical position of the cylindrical hole

inside the collimator. Only photons whose coordinates

lie on the hole on the first collimator surface and on the

hole on the second collimator surface will be able to

pass through the collimator hole. The parameters of the

collimator are following: Rc = 10 mm, ∆R = 3.5 mm

and rc = 0.45 mm.

Conclusions

From Monte Carlo simulations of the X-ray generation process in an X-ray tube with a conical target

(anode), several important parameters and dependences were determined: the X-ray spectra in the

acceleration potential range of 250-500 kV, the optimal target shape, the angular distribution of the

intensity of X-rays collimated through the cylindrical hole or slit of an external collimator and the

efficiency coefficient for energy transfer from an electron beam to a generated X-ray flux. It was

demonstrated that the angular distribution of the intensity in a collimated X-ray beam depends on the

radius of the electron beam and on the shape of the conical target and that these dependences are

different at different acceleration potentials of the X-ray tube. The optimal values of the geometrical

parameters of a scanning system based on an X-ray tube integrated with an external collimator were

observed to maximise the output X-ray intensity in the beam. These results and the proposed

methods for the numerical modeling of the external collimators can be used in practical applications

to design scanning systems based on the pencil-beam technique and X-ray tubes with massive conical

targets.

References

[1] G. Harding, J. Kosanetzky, Scattered X-ray beam nondestructive testing, NIM: Section A, 280, (1989), 517-528.

[2] D.N. Zeiger, J. Sun, G.E. Schumacher, S.L. Gibson, Evaluation of dental composite shrinkage and leakage in extracted teeth using X-ray microcomputed

tomography, Dental Materials, 25, (2009), 1213-1220.

[3] L. Goldstein, S.O. Prasher, S. Ghoshal, Three-dimensional visualization and quantification of non-aqueous phase liquid volumes in natural porous media

using a medical X-ray Computed Tomography scanner, J. of Contaminant Hydrology, 93, (2007), 96-110.

[4] M. Lindner, L. Blanquart, P. Fischer, H. Krüger, N. Wermes, Medical X-ray imaging with energy windowing, NIM: Section A, 465, (2001), 229-234.

[5] A. Ihsan, S.H. Heo, H.J. Kim, C.M. Kang, S.O. Cho, An optimal design of X-ray target for uniform X-ray emission from an electronic brachytherapy

system, NIM: Section B, 269, (2011), 1053-1057.

[6] G. Harding, B. Jordan and J. Kosanetzky, A new fluorescent X-ray source for photon scattering investigations, Phys. Med. Biol., 36, No.12 (1991), 1573.

[7] S. Henzell, S.S. Dhaliwal, R.I. Price, F. Gill, C. Ventourasa, C. Greena, F.D. Fonseca, M. Holzherr, R. Prince, Comparison of Pencil-Beam and Fan-

Beam DXA Systems, Journal of Clinical Densitometry, 6, (2003), 205-210.

[8] S. Humphries, Computational Techniques in Xenos - Integrated 3D Software Suite for Electron and X-ray Physics, IEEE 34th International Conference

ICOPS 2007, 729, 2007.

[9] F. Salvat, J.M. Fernández-Varea, J. Sempau, PENELOPE-2011: A code system for Monte Carlo simulation of electron and photon transport, OECD

Nuclear Energy Agency, 369, 2011.

[10] J.R. Taylor, An introduction to Error Analysis, University Science Books (1996).

[11] S.A. Ivanov, G.A.Shchukin, Rentgenovskie trubki tekhnicheskogo naznacheniya (X-ray Tubes for Technical Purposes), Leningrad: Energoatomizdat,

1989 [in Russian].

[12] H.W. Koch, J.W. Motz, Bremsstrahlung Cross-Section Formulas and Related Data, Rev. Mod. Phys., 31, 920, 1959.

[13] K.N. Mukhin, Nuclear physics (translated from Russian), Macdonald & Co., 505, 1970.

0 30 60 90 120 150 1800

2x107

4x107

6x107

8x107

50

150

300

450

550

X(

), p

hoto

ns/s

, degrees

Figure 2: The angular distributions of the intensity of collimated X-ray photons

(recalculated for a collimator with a hole) in cylindrical geometry at different

values of the apex angle of the anode when the electron energy is equal to 250 keV

and the electron beam radius is equal to 2.0 mm.