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Shielding for patient-scattered radiation from elekta precise
linear accelerator by Monte Carlo simulation
Cheung, Chi-wai; 張志偉
Cheung, C. [張志偉]. (2014). Shielding for patient-scattered
radiation from elekta precise linear accelerator by Monte Carlo
simulation. (Unpublished thesis). University of Hong Kong,
Pokfulam, Hong Kong SAR. Retrieved from
http://dx.doi.org/10.5353/th_b5303880.
2014
http://hdl.handle.net/10722/206509
The author retains all proprietary rights, (such as patent rights)
and the right to use in future works.
SHIELDING FOR PATIENT-SCATTERED RADIATION
FROM ELEKTA PRECISE LINEAR ACCELERATOR BY
MONTE CARLO SIMULATION
CHEUNG CHI WAI
MMedSc DISSERTATION
THE UNIVERSITY OF HONG KONG
2014
Shielding for Patient-Scattered Radiation From
Elekta Precise Linear Accelerator By Monte
Carlo Simulation
Submitted by
CHEUNG Chi Wai
for the degree of Master of Medical Sciences
at The University of Hong Kong
in August 2014
Abstract
In shielding design of a radiotherapy treatment room, the requirements of dose
limits outside the room must be fulfilled. The primary beam from the linear accelerator,
the leakage radiation from the gantry and the scattered radiation from the patient and
other objects contribute to the radiation exposure outside the room.
In this dissertation, we focused on the scattered radiation from the patient
irradiated by the primary radiation beam including 6, 10 and 25 MV from an Elekta
Precise linear accelerator. By using Monte Carlo simulations, we analysed the
characteristics of the scattered radiation, so that we have better understanding of the
scattered radiation when designing the shielding of a treatment room. The angular
distributions and energy spectrum of the scattered radiation are presented. It was found
that both the number of scatter particles and energy of the scatter particles increase with
increasing primary beam energy and decreasing scatter angle.
We also performed Monte Carlo simulations to collect the transmission data of
scattered particles passing through the shielding wall made of the concrete commonly
used in Hong Kong. The simulated results are tabulated and could be used for radiation
protection purposes for the estimation of the radiation exposure behind the shielding
concrete wall due to the patient scattered radiation.
Shielding for Patient-Scattered Radiation From
Elekta Precise Linear Accelerator By Monte
Carlo Simulation
By
CHEUNG Chi Wai
M.Phil (HKUST), BEng (HKUST)
A dissertation submitted in partial fulfilment of the requirements for
the Degree of Master of Medical Sciences
at The University of Hong Kong
August 2014
Declaration
I declare that this dissertation represents my own work, except where due
acknowledgement is made, and that it has not been previously included in a thesis,
dissertation or report submitted to this University or to any other institution for a degree,
diploma or other qualifications.
Signed …………………………………………..
i
Acknowledgements
I would like to express my most sincere gratitude to my supervisor Dr. Ben Ng.
Without his continuous support and valuable guidance in this year, I could not have
finished this dissertation.
I also want to thank all my teachers and classmates in the Master of Medical
Sciences program, who made my study interesting and rewarding.
Last but not least, I am indebted to my family and my girlfriend Ms. Janet Ng for
their love and support.
ii
Content
Declaration ..................................................................................................................................................... i
Acknowledgements ....................................................................................................................................... ii
Content ......................................................................................................................................................... iii
Chapter 1:
Introduction .......................................................................................................................... 1
References .................................................................................................................................................. 4
Chapter 2:
Monte Carlo Simulations for Shielding of Linear Accelerators ....................................... 6
2.1
Introduction ................................................................................................................................. 6
2.2
Monte Carlo Simulations in this dissertation .............................................................................. 7
2.3
Phase Space files ......................................................................................................................... 8
2.4
Secondary Collimators ...............................................................................................................10
2.5
Scoring .......................................................................................................................................10
2.6
References ..................................................................................................................................11
Chapter 3:
Patient-Scattered Radiation from Linear Accelerators....................................................13
3.1
Introduction ................................................................................................................................13
3.2
Monte Carlo Simulation Setup for studying the primary beams.................................................14
3.2.1
The Geometry Setup ...................................................................................... 14
3.2.2
The Water Phantom ...................................................................................... 15
3.2.3
The Beam Source .......................................................................................... 15
3.3
Dose Calibration for 6MV, 10MV and 25MV Photon Beams ....................................................16
iii
3.4
Characteristics of Primary Photon Beams .................................................................................18
3.4.1
Particles Energy Distributions ..................................................................... 18
3.4.2
Surface Dose in Water .................................................................................. 19
3.4.3
Central Axis Percentage Depth Dose in Water ............................................ 22
3.4.4
Beam Profiles ................................................................................................ 22
3.4.5
Discussion ..................................................................................................... 23
3.5
Monte Carlo Simulation Setup for studying the Patient-scattered Radiation ............................29
3.5.1
The Geometry Setup ...................................................................................... 29
3.5.2
The Patient Phantom..................................................................................... 30
3.6
Characteristics of Patient Scattered Radiation ..........................................................................31
3.6.1
Scatter Yields ................................................................................................ 31
3.6.2
Angular Distributions of Scatters ................................................................. 31
3.6.3
Energy Distributions of Scatters ................................................................... 34
3.7
Chapter 4:
References ..................................................................................................................................39
Transmission data of Patient-Scattered Radiation in Concrete ......................................40
4.1
Introduction ................................................................................................................................40
4.2
Monte Carlo Simulation Setup ...................................................................................................41
4.2.1
Concrete in Hong Kong ................................................................................ 41
4.2.2
The scatter particle source............................................................................ 41
4.2.3
The Geometry Setup ...................................................................................... 43
4.2.4
Variance Reduction ....................................................................................... 46
4.3
Results and Discussion ...............................................................................................................47
4.4
References ..................................................................................................................................59
iv
Chapter 5:
Conclusion ............................................................................................................................60
Appendix A: FLUKA Source Code ............................................................................................................62
A.1:
User Routine source.f for Reading IAEA phase space files ........................................................62
A.2:
User Routine mgdraw.f for Writing IAEA phase space files ......................................................70
A.3:
User Routine usrmed.f for Solving the particles double counting problem ................................75
A.4:
FLUKA input file for collecting Patient-Scattered Radiation ....................................................76
A.5:
FLUKA input file for collecting Transmission data of Patient-Scattered Radiation in Concrete
79
v
vi
Chapter 1:
Introduction
In shielding design of radiotherapy treatment rooms, the objective is to
reduce the radiation dose to the individuals outside the room to an acceptable low
level. In Hong Kong, the radiation ordinance [1] requires that the time-averaged
radiation dose rate of any point outside the room should not exceed 3 mSv per
hour.
There are three sources of radiations to be considered in shielding design
of radiotherapy treatment rooms: (1) the primary radiation beam from the linear
accelerator, which is used to treat the patients; (2) the leakage radiation from the
gantry of the linear accelerator; (3) the scatter radiation produced by the primary
beam irradiating the patients and other objects.
The methods of analytically calculating the required barrier transmission
factors for the primary, leakage and scatter radiations are explained in NCRP
151[2]. For the primary barrier, the calculation is based on the workload of the
linear accelerator W, the distance between the target and the point of measurement
d, the use factor U, the occupancy factor T and the dose limit P. For the secondary
barrier, both the leakage radiation and scatter radiation are considered. The barrier
transmission factor for the leakage is calculated similar to the primary barrier
except the use factor not taken into account. The barrier transmission factor for
scatter radiation Bscatter is calculated by
1
where a is scatter fraction; F is the area of the beam in the scatterer; dtarg-scat is the
distance between the target and the scatterer and dscat-meas is the distance between
the scatterer and the point of measurement. The thickness of the barrier is then
calculated by using the tenth value layer of the shielding material. This
formulation is simplified in certain extent. In this dissertation, we would like to
investigate using Monte Carlo simulations, the effect of the beam energy, field
size, and scattering angle on the scattered radiation produced from the patient as
well as the attenuation of the scattered radiation in concrete. Particularly, we focus
on the Elekta Precise linear accelerator and the concrete commonly found in Hong
Kong.
Monte Carlo simulations are commonly used in calculation of shielding
for radiotherapy treatment rooms. K.R. Kase et.al. calculated the leakage neutron
spectra and its attenuation in concrete using Monte Carlo simulations [3]. Peter J.
Biggs et.al. investigated the angle of obliquity for secondary radiation using
Monte Carlo simulations [4]. The obliquity factors listed in NCRP151 report are
results of Monte Carlo simulations [5]. S.A. Martinez-Ovalle et.al. calculated the
neutron dose equivalent in tissue using ICRU tissue phantom [6]. Stephen F Kry
et.al. used Monte Carlo simulations to calculate the vault shielding for flattening
filter free linear accelerator [7]. Adnan K. Jaradat et.al. estimated the tenth value
layer of concrete for small cone size radiation beam [8]. A. Facure et.al evaluated
different compositions of concrete in attenuating the primary beam [9].
S.
Agosteo et.al. estimated neutrons produced in proton accelerators and the
attenuation of the neutron in concrete and iron [10, 11].
2
This dissertation used the FLUKA Monte Carlo that incorporate the Phase
Space files as provided by IAEA for the simulation of the radiation beam output.
To our best knowledge, no Monte Carlo study exists focusing on the shielding of
the scattered radiation for linear accelerators using phase space files provided by
IAEA. This approach can yield general simulated results and are not confined to
an individual linear accelerator installed in the hospital.
This dissertation is organized as follows. This chapter 1 gives a brief
summary of the background and motivation of this study. In chapter 2, previous
works on applying Monte Carlo simulations in shielding of linear accelerators are
reviewed. In chapter 3, the method of simulating an Elekta Precise Linear
accelerator is described and Monte Carlo simulations are conducted to analyze the
characteristics of both the primary beams and the scattered radiations from
patients for various field sizes and energies available on the linear accelerator. In
chapter 4, the transmission of the patient scattered radiation through the shielding
concrete commonly used in Hong Kong is evaluated. Finally, chapter 5 gives the
conclusion of this dissertation.
3
References
[1] CAP 303B RADIATION (CONTROL OF IRRADIATING APPARATUS)
REGULATIONS,
http://www.legislation.gov.hk/blis_pdf.nsf/CurAllEngDoc/3643B9F10E66586F48
2575EE005B6BB7/$FILE/CAP_303B_e_b5.pdf
[2] Morgan, H., “NCRP Report 151 Structural shielding design and evaluation for
megavoltage x-and gamma-ray radiotherapy facilities”, Journal of Radiological
Protection, 2006
[3] Kase KR, Nelson WR, Fasso A, Liu JC, Mao X, Jenkins TM, Kleck JH,
“Measurements of accelerator-produced leakage neutron and photon
transmission through concrete”, Health Physics, 2003
[4] Peter J. Biggs and John R. Styczynski, “Do angles of obliquity apply to 30
degrees scattered radiation from megavoltage beams?”, Health Physics, 2008
[5] Peter J. Biggs, “Obliquity factors for 60 Co and 4, 10, and 18 MV x rays for
concrete, steel, and lead and angles of incidence between 0 and 70 degrees”,
Health Physics, 1996
[6] Martínez-Ovalle SA, Barquero R, Gómez-Ros JM, Lallena AM. ,“Neutron
dose equivalent and neutron spectra in tissue for clinical linacs operating at 15,
18 and 20 MV”, Radiation Protection Dosimetry, 2011
[7] Stephen F Kry, Rebecca M Howell, Jerimy Polf, Radhe Mohan and Oleg N
Vassiliev, “Treatment vault shielding for a flattening filter-free medical linear
accelerator”, Physics in Medicine and Biology, 2009
[8] Adnan K. Jaradat and Peter J. Biggs, “Tenth value layers for 60Co Gamma
Rays and For 4, 6, 10, 15, and 18 MV X Rays in Concrete for Beams of Cone
Angles between 0o and 14o Calculated by Monte Carlo Simulation”, Health
Physics, 2007
[9] A. Facure and A.X. Silva, “The use of high-density concretes in radiotherapy
treatment room design”, Applied Radiation and Isotope 65, 2007
[10] S. Agosteo, M. Magistris, A. Mereghetti, M. Silari, Z. Zajacova, “Shielding
data for 100–250 MeV proton accelerators: Double differential neutron
distributions and attenuation in concrete”, Nuclear Instruments and Methods in
Physics Research. Section B, Beam Interactions with Materials and Atoms,
2007
4
[11] S. Agosteo, M. Magistris, A. Mereghetti, M. Silari, Z. Zajacova, “Shielding
data for 100–250 MeV proton accelerators: Attenuation of secondary radiation
in thick iron and concrete/iron shields”, Nuclear Instruments and Methods in
Physics Research. Section B, Beam Interactions with Materials and Atoms,
2008
5
Chapter 2:
Monte Carlo Simulations for Shielding of
Linear Accelerators
2.1 Introduction
The applications of Monte Carlo simulations in radiotherapy treatment
room design are divided into two categories [1]. The first one is to apply the
Monte Carlo simulations directly to a model based on the designed room
geometry for calculating the dose distributions. The advantage of the method is
that the more detail is the model , the more accurate are the simulated results . The
disadvantage is that it is computing time costly to build up the model accurately
and the room design may change frequently in planning stage. In addition, the
computational cost is very high to fully simulate a treatment room, especially
when the model is very detail because of the particle tracking algorithms. The
method in the second approach is to use Monte Carlo simulations for computation
of the shielding parameters used in analytical calculations. Examples of the
shielding parameters include the tenth value layers [2] and obliquity factors [3].
The advantage of the method in this category is lower computational requirement.
In addition, the simulation does not need to re-run when the room design is
modified. NCRP report 151 [4] is of the second category, which defines the
analytical methods for calculations that incorporate the parameters computed by
Monte Carlo simulations.
6
The study in this dissertation is of the second category, which computes
the transmission data of patient scattered radiation of an Elekta Precise linear
accelerator for the concrete used in Hong Kong. This data helps to decide the
required thickness of the second barriers to fulfil the requirements in Radiation
Ordinance in Hong Kong (Cap 303b), and therefore is useful for design of
treatment rooms.
In this Chapter, some issues related to the Monte Carlo simulations in this
dissertation are described, which include the hardware, the Monte Carlo
simulation program and some simulation details.
2.2 Monte Carlo Simulations in this dissertation
There are a number of Monte Carlo simulation tools available for research.
Some of them are general purpose Monte Carlo particle transport system,
including MCNP [5], Geant4 [6] and FLUKA [7] etc. There are also some
simulation tools specifically designed for some purposes like radiotherapy
dosimetry [8] and proton therapy simulations [9].
In this dissertation, we used FLUKA for our simulations. FLUKA is
developed and maintained under an INFN-CERN agreement. The users need to
compose an input file which includes the FLUKA commands called cards and
pass the input file the FLUKA to start a simulation. An advanced user friendly
interface namely FLAIR [10] is provided to ease the editing of the input file.
FLAIR also provides visualization of the geometry and an additional material
database.
7
Throughout this dissertation, the Monte Carlo simulations were performed
using FLUKA Version 2011.2b in a dedicated computer with Intel® Core™ i74770K CPU, 8 GB DDR3 RAM and 500 GB solid state drive, which operating
system is Ubuntu 12.04 (64 bit).
It is desirable to run multiple simulations simultaneously to make good use
of the multi-core CPU. In the time of preparing this dissertation FLUKA does not
support multithreading unlike Geant4. (Geant4 supports multithreading starting
from Version 10.0) However, FLAIR provides tools for splitting one single
simulation into several jobs with different random seeds, and merging the result
files automatically afterwards.
It should be noted that 8 GB RAM is insufficient for running multiple simulations
in parallel (especially when the phase space files are preloaded into RAM).
Therefore the solid state drive is used as virtual memory instead of storage
because of its higher access speed comparing with Hard Disk drive and lower cost
comparing with DDR3 RAM
2.3 Phase Space files
In Monte Carlo simulations, the phase space represents the multidimension of the physical quantities of the particles in travel, which includes the
position, momentum and particles type etc. A phase space file stored the particles
in a Monte Carlo simulation which fulfill some user-defined criteria (e.g. passing
through plane or crossing the boundary between two objects). In FLUKA, the
term “collision tape” is used instead of “phase space file” because of historical
reasons.
8
Typically a phase space consists of two files: one header file and one phsp
file. The header file describes the number of primary particles, number of particles
stored in the phase space, the statistical summaries of the energy, type and
positions of the particles. The phsp file stores the types, positions and momentums
of individual particles.
The International Atomic Energy Agency (IAEA) holds a phase space
database for external beam Radiotherapy [11]. The phase space files in the IAEA
phase space database are in IAEA Phase Space format. In the IAEA phase space
database, the phase space files for several linear accelerators are available, which
include Varian Truebeam, Varian Clinac 600C, Varian Clinac iX, Elekta Precise,
Siemens Primus and Accuray CyberKnife. The phase space files can be
downloaded from their website and can be used to simulate the output of a linear
accelerator.
The format of the “collision tape” in FLUKA is different from that of
IAEA Phase Space files. By default, user can obtain a collision tape by inputting a
card USERDUMP. In FLUKA, reading and writing IAEA Phase Space files are
not natively supported. The user has to implement his own routines in the
framework provided in FLUKA. FLUKA is developed in Fortran and therefore
the user routines have to be implemented in Fortran.
However, the exact file format of the IAEA Phase Space file is not
publicly available. The IAEA NAPC Nuclear Data section and IAEA NAHU
Dosimetry and Medical Radiation Physics Section provided a set of read/write
routines for reading and writing IAEA Phase Space files. In most situations, the
users only need to link the library file built. However, if the users require
9
modification of the provided functions, the users need to modify the source code
and re-build the library. In our simulations, we implemented a source.f and a
mgdraw.f for reading the IAEA phase space files as particle sources and writing
phase space files in IAEA format respectively. The source codes of source.f and
mgdraw.f are given in appendix. The reading and writing routines of the IAEA
Phase space files for Geant4 have been already implemented [12].
2.4 Secondary Collimators
In the headers of the phase space files, it is mentioned that the phase space
are recorded just above the jaws and MLC. Therefore in our simulations, the jaws
are constructed for collimating the photon beams to define the field sizes. The
opening positions of the jaws should be set properly according to the specific field
size at 100 cm source to surface distance. For simplicity, the positions of the jaws
are set by taking into account the geometrical projection of the beam only. Firstly,
the jaws are inserted in a closed position. The jaws are then transformed using a
“ROT-DEFI” card which rotates the jaws at a particular angle around the origin,
which is calculated using the field size at 100 cm SSD. In reality the field size of a
linear accelerator should be calibrated using a film. In chapter 3, the field sizes are
verified visually. In case of studying patient scattered radiations the small
difference does not affect the result significantly.
2.5 Scoring
FLUKA supports scoring dose, energy, fluence etc. in a regular spatial
structures using USRBIN card or in a boundary between two regions using
USRBDX card. For each scoring card one result file will be generated after a
simulation finishes.
10
FLAIR supports splitting one simulation into several jobs for making good
use of the multi-core CPU. The result files are generated for each jobs. FLUKA
provides an utility executable namely “usxsuw” which combines the generated
scoring results of the USRBIN card. By default, the “usxsuw” tool assumes the
number of data points in one scoring result file is not more than 300000. To
enable the tool to combine the result files with more than 300000 primaries, the
parameter MXDUMM in “usxsuw.f” should be modified and the tools should be
recompiled using the provided makefile.
2.6 References
[1] Peter J. Biggs and Stephen F. Kry, “Monte Carlo for Shielding of
Radiotherapy Facilities”, Monte Carlo Techniques in Radiation Therapy,
Taylor & Francis 2013
[2] Adnan K. Jaradat and Peter J. Biggs, “Tenth value layers for 60Co gamma
rays and for 4, 6, 10, 15, and 18 MV x rays in concrete for beams of cone
angles between 0 degrees and 14 degrees calculated by Monte Carlo
simulation”, Health Physics, 2007
[3] Peter J. Biggs, “Obliquity factors for 60 Co and 4, 10, and 18 MV x rays for
concrete, steel, and lead and angles of incidence between 0 and 70 degrees”,
Health Physics, 1996
[4] Morgan, H., “NCRP Report 151 Structural shielding design and evaluation for
megavoltage x-and gamma-ray radiotherapy facilities”, Journal of Radiological
Protection, 2006
[5] X-5 Monte Carlo Team, “MCNP - A General N-Particle Transport Code,
Version 5” Volume I: Overview and Theory, LA-UR-03-1987 (2003, updated
2005).
[6] Allison, J., Amako, K., Apostolakis, J. et.al. “Geant4 developments and
applications”, IEEE Transactions on Nuclear Science 53, 2006
[7] G. Battistoni, S. Muraro, P.R. Sala, F. Cerutti, A. Ferrari, S. Roesler, A. Fasso`,
J. Ranft, "The FLUKA code: Description and benchmarking", Hadronic
Shower Simulation Workshop 2006
11
[8] GATE, Simulations of Preclinical and Clinical Scans in Emission
Tomography, Transmission Tomography and Radiation Therapy,
http://www.opengatecollaboration.org/
[9] Perl J, Shin J, Schumann J, Faddegon B, Paganetti H., “TOPAS: an innovative
proton Monte Carlo platform for research and clinical applications”, Medical
Physics, 2012
[10] V.Vlachoudis "FLAIR: A Powerful But User Friendly Graphical Interface
For FLUKA", Int. Conf. on Mathematics, Computational Methods & Reactor
Physics (M&C 2009), 2009
[11] Phase-space database for external beam radiotherapy, IAEA NAPC Nuclear
Data Section, IAEA NAHU Dosimetry and Medical Radiation Physics Section,
http://www-nds.iaea.org/phsp/phsp.htmlx
[12] Cortés-Giraldo MA, Quesada JM, Gallardo MI, Capote R, “An
implementation to read and write IAEA phase-space files in GEANT4-based
simulations”, International Journal of Radiation Biology, 2012
12
Chapter 3:
Patient-Scattered Radiation from Linear
Accelerators
3.1 Introduction
In this chapter, we study the characteristics of the scatter radiation induced
from the patient for different beam energy and field size using Monte Carlo
simulations.
Firstly, the setup of the Monte Carlo simulations for studying the
characteristics of the primary beams are described, which includes the geometry,
the water phantom, and beam sources. The primary beams of different energy are
then calibrated with the water phantom measurements. The characteristics of the
primary beams in our simulations are studied, which include the particle energy
distributions, surface dose in water, percentage depth dose and beam profiles.
The setup of the Monte Carlo simulations for studying the characteristics
of the patient-scattered radiations are described, which include the geometry,
patient phantom and material compositions. The characteristics of the patientscattered radiations are studied, which include scatter yields and scatter energy
distributions.
13
3.2 Monte Carlo Simulation Setup for studying the
primary beams
3.2.1 The Geometry Setup
The Geometry setup for dose calibration is illustrated in Fig 3-1. The
primary beam is firstly collimated by Y-jaw and X-jaw, which material is
tungsten [1]. For simplicity, only Y-jaws are modeled to collimate the Y edge of
the field, instead of a MLC & Y backup jaws combination. Then beam particles
pass through a thin Mylar crosswire sheet.
Fig. 3-1 Geometry Setup for studying the characteristics of the primary beams and dose
calibration of the primary beams
14
3.2.2 The Water Phantom
The size of the water phantom matches with the scanning volume of the
IBA blue phantom which is 480mm x 480 mm x 480 mm [2]. We use 100 cm
Source Surface Distance (SSD) for studying the characteristics of the primary
beams and dose calibration of the primary beams, meaning that the water phantom
is set at 100cm from the beam source position. The positions of the jaws are set so
that the field size of the beam at water surface is 10cm x 10cm. Pure water (H20)
is used to fill the water phantom.
3.2.3 The Beam Source
The phase space files provided in the IAEA phase space database [3] are
used to simulate the beam source of the Elekta Precise linear accelerator. In the
database, for the Elekta Precise linear accelerator, the phase space files for 6MV,
10MV and 25MV are available to download. The statistics summary of the phase
space files are listed in Table 3-1.
Table 3-1 statistics summary of the phase space files
6MV
10MV
Energy
Number of original
25MV
680000000
335000000
200000000
Number of particles
505900790
503494019
568008047
Number of photons
503158953
498823611
557375711
Number of electrons
2684439
4413277
9021165
Number of positrons
57398
257131
1611171
Phase space position
z = 27.21 cm
z = 27.21 cm
z = 27.21 cm
5.75 MeV
9.4 MeV
19.0 MeV
0.15 cm
0.118 cm
0.447 cm
histories
Energy of initial
electrons
Spot size (FWHM)
15
3.3 Dose Calibration for 6MV, 10MV and 25MV Photon
Beams
In radiotherapy, a machine unit (MU) is a measure of radiation output of a
linear accelerator, which is measured by a built-in ionization chamber. The linear
accelerators are commonly calibrated to display 1 MU for 1cGy in a point of
maximum dose in central axis in water in a 100cm SSD setup for 10cm x 10cm
field at water surface [4].
In our study, it is important to establish a relationship between the machine
units and the number of particles in the phase space files provided in the IAEA
phase space database, so that the data presented in this dissertation is traceable to
the number of MU in reality. We adopt the definition mentioned above as the
definition of MU in this dissertation. The central axis depth dose curves are
measured for 6MV, 10MV and 25MV beam with field size 10cm x 10cm.
Number of primaries used in each setting is 4E-8. The central axis depth dose
curves are shown in Figure 3-2. The MU – Particles in the phase space files
relationships are summarized in Table 3-2.
Table 3-2 Relationship between the machine units and the number of particles in the phase
space files provided in the IAEA phase space database
6MV
10MV
25MV
Dose at max dose
1.36410128E-8
1.71641972E-8
2.7518583E-8
point/particles in
GeV/g
GeV/g
GeV/g
4575546877369
3636353785150
2268107097331
Energy
phase space files
Number of particles
gives 1 MU
16
Fig. 3-2 Depth dose curve for (a) 6MV, (b) 10MV and (c) 25MV for 10cm x10cm field size.
17
3.4 Characteristics of Primary Photon Beams
For each energy and field size setting, 4E+8 primaries are randomly drawn
from the IAEA Phase Space files. It should be noted that the results presented in
this section are “per primary in phase space files in IAEA phase space”. The
correspondence between the number of primaries in phase space files in IAEA
phase space and machine units can be found in Section 3.3.
3.4.1 Particles Energy Distributions
The Energy distributions of the photons and electrons of the beam
collimated by the XY jaws and passed through the thin Mylar crosswire sheet for
different energy and different field size are shown in Figure 3.3. The percentage
errors for all data points are less than 0.84%.
It should be noted that the results are presented in particles/GeV/primary.
To estimate the exact number of particles within an energy range, the values in the
figure should be multiplied by the width of the energy range. For example, the
number of photons with energy 0.0003GeV-0.0004GeV per primary for 6MV
beam with 40cm x 40cm field size is 0.0001*473 = 0.0473.
The energy distributions of the photons and electrons do not change much
for the same beam energy, except the number of the particles increases with the
field size. The peak energy of the photons decrease with increasing field size.
18
3.4.2 Surface Dose in Water
For MV photon beams, the surface dose is lower than the maximum dose.
Therefore, visualizing the surface dose in the water helps to verify the setting of
the jaws for specific field sizes. In our simulation, the surface dose is measured on
the 0-0.5 cm depth in water. The 2D distributions of the surface dose for different
energy and field size are shown in Figure 3-4.
19
Electron distributions for 6MV
electrons/GeV/prinary
photons/GeV/prinary
Photon distributions for 6MV
Electron distributions for 10MV
electrons/GeV/prinary
photons/GeV/prinary
Photon distributions for 10MV
Electron distributions for 25MV
photons/GeV/prinary
electrons/GeV/prinary
Photon distributions for 25MV
Fig. 3-3 Energy Distributions for Photons and Electrons for 6 MV, 10 MV and 25 MV for
different field size.
20
6MV
10MV
Fig. 3-4 2D distributions of the surface dose for different energy and field size
21
25MV
3.4.3 Central Axis Percentage Depth Dose in Water
The central axis percentage depth dose curves for different field size and
energy are shown in Fig 3-5. The curves are consistent with our knowledge that
the depth of the maximum dose increases with increasing energy and decreasing
field size [5].
3.4.4 Beam Profiles
The beam profiles are measured in water surface and at 10 cm depth under
water. The X and Y beam profiles in water surface are shown in Figure 3.6 and
3.7. The X and Y beam profiles at 10 cm depth under water are shown in Figure
3.8 and 3.9. It is observed that for the same energy and field size the penumbra at
10 cm depth under water are larger than the penumbra in water surface because of
the scattering in water (Scatter penumbra). The penumbra in Y direction is larger
than the penumbra in X direction because the distance from the Y jaws to the
water is large than the distance from the X jaws to the water (Geometric
penumbra). The penumbra increases with the beam energy because of the
increased number of particles transmission through the jaws (transmission
penumbra) and the higher energy of the scattered radiation [5].
22
3.4.5 Discussion
The percentage depth dose and beam profiles should be compared with the
measurement data for validation. However, because of the unavailability of
retrieving the measurement data of the linear accelerator, we performed
comparisons for the percentage depth dose for 6MV and 10MV only, and result
shows that the differences of the percentage depth dose are within 6%. Therefore,
in this dissertation, the rationality of simulating the output of the Elekta precise
linear accelerator using the phase space files relies on both the validation of the
phase space files by IAEA and the visualization check of the percentage depth
dose and beam profiles generated by the simulations.
23
Fig. 3-5 The central axis percentage depth dose curves for different field size
and energy
24
Fig. 3-6 X beam profiles in water surface for different field size and energy
25
Fig. 3-7 Y beam profiles in water surface for different field size and energy
26
Fig. 3-8 X beam profiles at 10cm depth in water for different field size and energy
27
Fig. 3-9 Y beam profiles at 10cm depth in water for different field size and energy
28
3.5 Monte Carlo Simulation Setup for studying the
Patient-scattered Radiation
3.5.1 The Geometry Setup
The Geometry setup for studying the characteristics of the patientscattered radiation is illustrated in Fig 3-10. The setup is similar to the setup used
in dose calibration. The only difference is that instead of placing a water cubic at
100 cm SSD, a patient phantom is placed at 100 cm SAD. The settings for the
jaws and the thin Mylar crosswire sheet remain unchanged.
Fig. 3-10 Geometry Setup for studying the characteristics of the patient-scattered
radiations
29
3.5.2 The Patient Phantom
The Patient phantom is a 40cm-diameter sphere filled with ICRP soft
tissue to simulate the human body. The elemental composition of the ICRP soft
tissue is provided in the material database in FLAIR and is verified using the
composition database provided in NIST [6]. The composition is listed in Table 33. The density is 1 g/cm^3 and the mean excitation energy is 72.3 eV
Table 3-3 Elemental Composition of ICRP soft tissue
Atomic number
Element
Fraction by mass
1
Hydrogen
10.4472%
6
Carbon
23.219%
7
Nitrogen
2.488%
8
Oxygen
63.0238%
11
Sodium
0.113%
12
Magnesium
0.013%
15
Phosphorus
0.133%
16
Sulfur
0.199%
17
Chlorine
0.134%
19
Potassium
0.199%
20
Calcium
0.023%
26
Iron
0.005%
30
Zinc
0.003%
30
3.6 Characteristics of Patient Scattered Radiation
For each energy and field size setting, 8E+9 primaries are randomly drawn
from the IAEA Phase Space files. It should be noted that the results presented in
this section are “per primary in phase space files in IAEA phase space”. We study
the characteristics of the patient-scattered radiation for different energy, field size
and scattering angle.
3.6.1 Scatter Yields
The Scatter Yields of the beam with different energy and field size are listed
in Table 3-4. It includes all particle types of the scattered radiation. The scattered
yields are important because in studying the transmission data of the scatters, the
results presented are “per scatter”.
Table 3-4 Total scatter yields per primary in phase space files in IAEA database
4cmx4cm
10cmx10cm 20cmx20cm 30cmx30cm 40cmx40cm
6 MV
0.00493365
0.03274058
0.140912
0.337056
0.503892
10MV
0.00508864
0.03343176
0.141532
0.326607
0.476717
25MV
0.00592395
0.04053351
0.171951
0.39573
0.566339
3.6.2 Angular Distributions of Scatters
The angular distributions of the scattered photons are shown in Figure 311. Five angular ranges are considered (0-10 degree, 40-50 degree, 85-95 degree,
130-140 degree & 170-180 degree). “0-10 degree” refers to the forward scatters,
“40-50 degree”, “85-95 degree” & “130-140 degree” refers to side scatters and
“170-180 degree” refers to the backscatters. It should be noted that for a particular
setting of energy and field size, the numbers of the scattered photons does not add
31
up to unity because some scattered photons are in directions which are not
included in the five angular ranges in this study and some injected particles are
absorbed by the water phantom.
It is observed that the for field size smaller than 20cm x 20cm the angular
distributions of the scatters are similar for a particular beam energy. For field size
larger than 20cm x 20cm, the numbers of forward scatters significantly reduced.
In addition, the higher the beam energy, the larger the fraction of forward scatters.
32
Fig. 3-11 Angular distributions of the scattered photons for different energy and field size.
33
number of scattered photons/primaty
number of scattered photons/primaty
number of scattered photons/primaty
3.6.3 Energy Distributions of Scatters
The energy distributions for the scatters from 6MV, 10MV and 25MV
with field size 10cm x 10cm are shown in Figure 3-12. It should be noted the
results presented are normalized to the numbers of scatters generated the primary
particles.
It is observed that the energy of forward scatters is much higher than other
scatters. For the beam energy in this study, the nominal energy of the primary
photons are between 0.1MeV and 10MeV, in which the Compton scattering
dominates the interactions of the photons in low atomic numbers materials, which
is the case of our phantom. In Compton scattering, the energy of scattered photon
decreases with the scattering angle. It explains our observation that the energy of
forward scatters is much higher than other scatters.
The energy distributions for the scatters for different field sizes for 6MV,
10MV and 25MV are shown in Figure 3-13, 3-14 and 3-15 respectively.
34
photons/GeV/prinary
photons/GeV/prinary
photons/GeV/prinary
Fig. 3-12 Energy distributions for the scatters from 6MV, 10MV and 25MV with field
size 10cm x 10cm
35
Fig. 3-13 Energy distributions for the scatters for different field sizes for 6MV
36
fluence/scatter in all directions
fluence/scatter in all directions
fluence/scatter in all directions
fluence/scatter in all directions
fluence/scatter in all directions
Fig. 3-14 Energy distributions for the scatters for different field sizes for 10MV
37
fluence/scatter in all directions
fluence/scatter in all directions
fluence/scatter in all directions
fluence/scatter in all directions
fluence/scatter in all directions
Fig. 3-15 Energy distributions for the scatters for different field sizes for 25MV
38
fluence/scatter in all directions
fluence/scatter in all directions
fluence/scatter in all directions
fluence/scatter in all directions
fluence/scatter in all directions
3.7 References
[1] Kadziolka, E.; Kisielewska-Birycka, M.; Surowiak, T.; Barszczewski, J.
Kukolowicz, P. F., “Information about the first Elekta Precise® accelerator
installed”, Reports of Practical Oncology and Radiotherapy, 2006
[2] IBA Blue phantom2, http://www.iba-dosimetry.com/
[3] Phase-space database for external beam radiotherapy, IAEA NAPC Nuclear
Data Section, IAEA NAHU Dosimetry and Medical Radiation Physics Section,
http://www-nds.iaea.org/phsp/phsp.htmlx
[4] Mayles, Philip; Nahum, Alan; Rosenwald, Jean-Claude, “From Measurements
to Calculations”, Handbook of Radiotherapy Physics - Theory and Practice, 2007
[5] E.B. Podgorsak, “External Photon Beams: Physical Aspects”, Radiation
Oncology Physics: A Handbook for Teachers and Students. IAEA 2005
[6] NIST Standard Reference Databases: Materials,
http://www.nist.gov/srd/materials.cfm
39
Chapter 4:
Transmission data of Patient-Scattered
Radiation in Concrete
4.1 Introduction
The characteristics of the scattered radiation induced from the patient for
different beam energy and field size are studied in Chapter 3. In this chapter, we
focused on the estimation of shielding parameters of the patient-scattered
radiations, such that the shielding parameters can be used directly in designing the
shielding of a treatment room for installing an Elekta Precise linear accelerator.
More specifically, we apply Monte Carlo simulations to estimate the attenuation
of the patient-scattered radiations through a wall which is made of a kind of
concrete commonly found in Hong Kong.
Firstly, the setup of the Monte Carlo simulations for estimating the
attenuation of the patient-scattered radiations through a concrete wall is described,
which includes the composition of the concrete commonly used in Hong Kong,
the scatter particle source, the geometry and variance reduction techniques used in
the simulations.
The simulation results are then presented and the use of the results in
designing the shielding of a treatment room for installing an Elekta Precise linear
accelerator will be discussed.
40
4.2 Monte Carlo Simulation Setup
4.2.1 Concrete in Hong Kong
A sample of concrete which was found in Hong Kong was sent to an ISO
9001:2008-certified laboratory for elemental testing. The elemental testing was
performed using polarized light microscopy, reflected light microscopy, x-ray
diffraction spectrometry, x-ray fluorescence spectrometry, thermal gravimetric
analysis and carbon/sulfur analysis. The resultant elements together with their
corresponding concentrations and the density in the sample were input as a
COMPOUND in the material database in FLAIR, so that we can insert the
elemental compositions of the concrete into our simulations.
The density of the sample is 2.4 g/cm3, which is slightly higher than that of
other standard concrete compositions like TSF-5.5 [2] (2.31 g/cm3) and NBS-04[3]
(2.35 g/cm3). The composition of the sample is sample is similar to that of TSF5.5, except that it contains less silicon and more calcium.
4.2.2 The scatter particle source
In studying the attenuation of the patient-scattered radiations, the most
straightforward approach is to define the primary beam source from the phase
space files provided in IAEA phase space database. The beam particles are then
collimated by the jaws, passing through the thin Mylar crosswire sheet, and reach
the patient phantom. The particles then interacted with the patient phantom, and
the scattered radiation propagated to the surrounding walls. The number of
particles passing through a wall are recorded and the results can be used to
analyze the attenuation of the scattered particles through the wall. The weakness
41
of this approach is that a large amount of computational power is spent on the
interaction between the beam particles and the components like the jaws and
patient phantom before reaching the concrete wall.
In this study we adopt another approach which the beam source is the
patient-scattered radiations directly. To facilitate this, the geometry described in
section 3.5 is used to produce the scatters and the scattered particles passing
through the surface of the patient phantom are stored into a phase space file in
IAEA phase space format. The phase space file can then be used as the particle
sources for studying the attenuation of the patient-scattered radiations.
However, applying this approach raises a particle double counting problem.
The problem is described as follows: when a particle scatters out and passes
through the surface of the patient phantom, the particle is stored into the phase
space file. If the particle is scattered back the phantom and scattered out again, the
particle will be stored into the phase space file again. In this case the particle is
double counted. In the FLUKA user manual [1], it is recommended to assign the
material “blackhole” to the regions behind the recording boundary. The material
“blackhole” in FLUKA absorbs all the particles entering the regions of it. As the
particles going behind the recording boundary are absorbed, there are no
backscattered particles and the problem will not occur.
However, in our settings the solution recommended in the FLUKA manual
does not apply because the primary beam injects into the patient phantom through
the regions surrounding it. If the regions surrounding the patient phantom are
42
assigned to the material “blackhole”, then the particles of the primary beam
cannot reach the patient phantom.
Therefore, we tackle this problem by another approach which makes use of
the user routine “usrmed.f” in FLUKA. “usrmed.f” is a user routine provided in
FLUKA, which will be called in every step in which the particles pass through the
materials selected by a MAT-PROP card inserted in the input file. Through
implementing the “usrmed.f” user routine, the user can modify the direction,
energy and weight of the particles. In our application, we implement the
“usrmed.f” such that the weights of all the particles transporting from the patient
phantom to the air are set to zero. The result is that the particles will be killed after
scattering from the patient phantom and therefore will not backscatter back to the
patient phantom and not be recorded twice. The source code of the “usrmed.f” is
given in the appendix.
For beam energy 6MV, 10MV and 25MV, and field size 4cm x 4cm, 10cm
x 10cm, 20cm x 20cm, 30cm x 30cm and 40cm x 40cm, 2.4E+9 primaries from
the phase space files are transported in the setting specified in section 3.5 and the
phase space files for the scatters are stored. Totally 19 days are used for running
the simulations and the total file size of the phase space files is 307GB.
4.2.3 The Geometry Setup
The Geometry setup for estimating the attenuation of the patient-scattered
radiations through a concrete wall is illustrated in Fig 4-11. The design of the
43
spherical wall is similar to [2,4] which studies the shielding data for proton
accelerators. The spherical design eliminates the need of handling the angle of
obliquity [5] which is beyond the scope of this dissertation. The portion of the
wall other than (0-10 degree, 40-50 degree, 85-95 degree, 130-140 degree & 170180 degree) is filled by the material “blackhole” to kill the particles which
transported out of the region of our interest for speeding up the simulations.
Fig. 4-1 Geometry Setup for estimating the attenuation of the patient-scattered radiations
through a concrete wall
44
45
4.2.4 Variance Reduction
Although the material “blackhole” is assigned into the geometry to speed
up the simulations, calculating the attenuation of scatters in concrete is still very
computational costly and time consuming. For example, because of the low
energy of the backscatters, on average only one backscattered particle can pass
through a 1.5m thickness concrete wall if 1E+11 backscattered particles are
injected into the wall. Therefore some variance reduction techniques must be used
to speed up the simulations or reduce the number of primary particles to produce
desired results. FLUKA provides a lot of variance reduction options, and the one
used in our study is Importance biasing. In importance biasing, relative
importance scores are assigned to the regions, and when the particles pass through
the boundary of two regions it may split into several particles or may be killed,
which depends on the importance scores of the two regions. We divide the wall
into several layers and tune the importance scores of the layers such that less
particles are required to inject to the wall.
46
4.3 Results and Discussion
The fluences in the concrete wall produced by the patient scatters from the
6MV, 10MV & 25MV beam energies and 4cmx4cm, 10cmx10cm, 20cmx20cm,
30cmx30cm & 40cmx40cm field sizes are scored for scattering angles (0-10
degree, 40-50 degree, 85-95 degree, 130-140 degree & 170-180 degree).
The ambient dose equivalents behind the wall with different thickness are
also estimated. The ambient dose equivalent estimations are done by folding the
fluences of different types and energies of particles with the conversion
coefficients [6]. FLUKA provides a built-in scorer for this purpose. The
conversion coefficients used in this study were from ICRP 74 and Pelliccioni data.
The fluences and ambient dose equivalents behind the wall with different
thicknesses for patient-scattered radiations for different beam energy, field size
and scattering angle are plotted in Figure 4-2 and the numerical values are listed
in Table 4-1. It is observed that both the fluences and ambient dose equivalents in
the wall increases with increasing beam energy and field size. The smaller is the
scattering angle, the higher are the fluences and ambient dose equivalents in the
wall. The attenuation curves of the 130-140 degree and 170-180 degree are similar,
because the energy distribution of the scatters from these two angular ranges are
similar (ref. to section 3.6.3).
It should be noted that the results presented in Table 4-1 are “per scatter
particles”. To estimate the fluences and ambient dose equivalents produced in an
Elekta Precise linear accelerator for given dose rate, beam energy, field size, wall
thickness and scattering angle, the user should firstly refer to section 3.3 to
47
estimate the corresponding number of the primaries in the phase space files. The
user then should estimate the number of scatters produced by using the tables in
section 3.6.1. The transmission data presented in the section (Table 4-1) can then
be used to for calculating the fluences and ambient dose equivalents.
For example, suppose we would like to estimate the scattered dose behind
a 30 cm thick wall at 45o to the 10MV beam with field size 10cm x 10cm for
200MU. From Table 3-2, we know 200MU is equivalent to 7.27E+14 particles in
phase space provided in IAEA database. For Table 3-4, we estimate the number of
scatter particles as 2.43E+13. From Table 4-1, we can estimate the ambient dose
equivalent due to the patient scattered radiation behind 30 cm concrete as 2.14uSv.
Other factors like angle of obliquity and the distance from the patient to the wall
should be further corrected.
The Tenth Value Layers (TVL) for patient-scattered radiations for
different beam energy, field size and scattering angle, which are derived from the
photon fluences passing through the concrete, are listed in Table 4-2. The TVLs
published in NCRP 151 [7] for 10, 45, 90 and 135 degrees are also included in
Table 4-2. For easy comparison, the data is presented in g/cm2. It is observed that
the TVLs published in NCRP 151 are larger than the values computed in our
simulations, because the TVLs listed in NCRP 151 are conservatively safe.
In this dissertation, the concrete wall is designed in a spherical geometry
to eliminate the need of handling the angle of obliquity. The angle of obliquity for
patient scattered radiation is not addressed in NCRP reports. Biggs PJ et. al [8]
studied the angle of obliquity for 30 degree scattered radiation and reported that
the angle of obliquity for a 30 angle relative to the normal of the concrete wall is
48
21.7 degree. The applicability of angle of obliquity is unknown for the angles
considered in this dissertation and is beyond the scope of this dissertation.
Neutrons will be generated if photons with energy higher than 10MeV
interact with materials of high atomic numbers. Therefore, there should be some
neutrons generated in the gantry head for 10MV and 25MV beams. However, the
phase space file provided by IAEA does not include the neutrons from the target
and in our simulation the metallic components in the gantry head are not modelled.
Therefore our simulations does not take into account the leakage neutrons.
Neutrons are also generated in concrete. However, referring to Section 3.6.3, the
energy of the photons reaching the concrete is low and therefore this study does
not separately consider the doses generated by the scatters interacting with the
concrete wall.
49
Table 4-1 The Fluence and Ambient Dose Equivalent behind the wall with different
thicknesses and scattering angles
6MV
4x4cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
1.7E-05 1.2E-06 1E-06 2.7E-07 2.8E-07 0cm
0.00015 2.9E-06 1.4E-06 1.9E-07 1.9E-07
1.5E-05 4.5E-07 2.6E-07 2.1E-08 1.9E-08 10cm
9.2E-05 1E-06 3.3E-07 1.6E-08 1.3E-08
8.6E-06 1.3E-07 4.3E-08 1.5E-09 1.1E-09 20cm
4.7E-05 3.1E-07 5.5E-08 1.2E-09 8.8E-10
4.4E-06 3.7E-08 6.8E-09 1.2E-10 7.8E-11 30cm
2.3E-05 8.8E-08 8.6E-09 1.1E-10 7.1E-11
2.2E-06 1E-08 1.1E-09 1.1E-11 7.2E-12 40cm
1.1E-05 2.5E-08 1.4E-09 1.2E-11 7.8E-12
1.1E-06 2.9E-09 1.6E-10 1.2E-12 8.6E-13 50cm
5.5E-06 7.1E-09 2.2E-10 1.4E-12 1.1E-12
5.1E-07 8.3E-10 2.6E-11 1.6E-13 1.2E-13 60cm
2.7E-06 2E-09 3.6E-11 2.1E-13 1.8E-13
2.5E-07 2.4E-10 4.4E-12 2.5E-14 2.2E-14 70cm
1.3E-06 5.9E-10 6.4E-12 3.9E-14 3.6E-14
1.2E-07 6.8E-11 7.4E-13 4.6E-15 4.1E-15 80cm
6.3E-07 1.7E-10 1.2E-12 8E-15 7.8E-15
5.8E-08 2E-11 1.4E-13 8.5E-16 9.2E-16 90cm
3.1E-07 5.1E-11 2.8E-13 1.7E-15 2E-15
2.8E-08 5.8E-12 3.3E-14 1.8E-16 2.4E-16 100cm 1.5E-07 1.5E-11 7.8E-14 4.2E-16 6.5E-16
1.4E-08 1.7E-12 8.7E-15 5.2E-17 7.2E-17 110cm 7.3E-08 4.6E-12 2.5E-14 1.4E-16 2.1E-16
6.7E-09 5.2E-13 2.7E-15 1.8E-17 2.2E-17 120cm 3.6E-08 1.4E-12 8.9E-15 4.4E-17 6.7E-17
3.3E-09 1.6E-13 9.4E-16 5.8E-18 7.4E-18 130cm 1.8E-08 4.4E-13 3.4E-15 1.4E-17 2E-17
1.6E-09 5E-14 3.5E-16 1.6E-18 2.1E-18 140cm 8.6E-09 1.4E-13 1.3E-15 4.1E-18 6.3E-18
7.7E-10 1.6E-14 1.4E-16 1E-18 6.8E-19 150cm
4E-09 4.4E-14 5.2E-16 1.5E-18 2.1E-18
6MV
10x10cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
1.6E-05 1.2E-06 1E-06 2.7E-07 2.9E-07 0cm
0.00014 2.8E-06 1.4E-06 1.9E-07 1.9E-07
1.5E-05 4.5E-07 2.6E-07 2.1E-08 1.9E-08 10cm
8.8E-05 1E-06 3.2E-07 1.6E-08 1.3E-08
8.3E-06 1.3E-07 4.2E-08 1.4E-09 1.1E-09 20cm
4.5E-05 3E-07 5.4E-08 1.2E-09 8.6E-10
4.2E-06 3.5E-08 6.6E-09 1.1E-10 7.6E-11 30cm
2.2E-05 8.4E-08 8.5E-09 1E-10 6.9E-11
2.1E-06 9.9E-09 1E-09 1.1E-11 6.9E-12 40cm
1.1E-05 2.4E-08 1.3E-09 1.1E-11 7.4E-12
1E-06 2.8E-09 1.6E-10 1.2E-12 7.9E-13 50cm
5.2E-06 6.7E-09 2.1E-10 1.4E-12 9.8E-13
4.9E-07 7.8E-10 2.5E-11 1.6E-13 1.1E-13 60cm
2.5E-06 1.9E-09 3.3E-11 2.2E-13 1.7E-13
2.3E-07 2.2E-10 4E-12 2.5E-14 2E-14 70cm
1.2E-06 5.5E-10 5.7E-12 4E-14 3.9E-14
1.1E-07 6.4E-11 6.8E-13 4.4E-15 5.6E-15 80cm
5.9E-07 1.6E-10 1E-12 8.7E-15 1.1E-14
5.4E-08 1.9E-11 1.2E-13 9.3E-16 1.5E-15 90cm
2.9E-07 4.7E-11 2.1E-13 2.2E-15 3.5E-15
2.6E-08 5.4E-12 2.4E-14 2.6E-16 3.4E-16 100cm 1.4E-07 1.4E-11 4.7E-14 6.4E-16 9.6E-16
1.3E-08 1.6E-12 5.5E-15 7.4E-17 1.1E-16 110cm 6.8E-08 4.2E-12 1.3E-14 2E-16 3.1E-16
6.2E-09 4.9E-13 1.5E-15 1.9E-17 4.3E-17 120cm 3.3E-08 1.3E-12 3.8E-15 5.2E-17 1.1E-16
3E-09 1.5E-13 4.1E-16 5.8E-18 1.4E-17 130cm 1.6E-08 4E-13 1.2E-15 1.6E-17 3.6E-17
1.5E-09 4.6E-14 1.3E-16 2.1E-18 4E-18 140cm 7.9E-09 1.3E-13 4E-16 5.3E-18 1.1E-17
7.2E-10 1.4E-14 4.6E-17 5E-19 1.3E-18 150cm 3.9E-09 4E-14 1.4E-16 1.5E-18 3.5E-18
6MV
20x20cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
1.7E-05 1.3E-06 1E-06 2.6E-07 2.7E-07 0cm
0.00014 2.9E-06 1.3E-06 1.8E-07 1.8E-07
1.5E-05 4.6E-07 2.5E-07 1.9E-08 1.8E-08 10cm
8.6E-05 1E-06 3.2E-07 1.5E-08 1.3E-08
8E-06 1.3E-07 4.1E-08 1.3E-09 1.1E-09 20cm
4.3E-05 3E-07 5.2E-08 1.1E-09 8.7E-10
4E-06 3.6E-08 6.4E-09 1.1E-10 8.2E-11 30cm
2.1E-05 8.5E-08 8.2E-09 9.8E-11 7.6E-11
1.9E-06 1E-08 1E-09 9.9E-12 7.7E-12 40cm
1E-05 2.4E-08 1.3E-09 1E-11 8.2E-12
9.2E-07 2.8E-09 1.5E-10 1.1E-12 9.2E-13 50cm
4.8E-06 6.9E-09 2E-10 1.3E-12 1.1E-12
4.4E-07 8.1E-10 2.4E-11 1.4E-13 1.3E-13 60cm
2.3E-06 2E-09 3.2E-11 1.9E-13 1.8E-13
2.1E-07 2.3E-10 3.8E-12 2.4E-14 2E-14 70cm
1.1E-06 5.8E-10 5.4E-12 3.6E-14 3E-14
1E-07 6.7E-11 6.4E-13 4.1E-15 3.5E-15 80cm
5.3E-07 1.7E-10 9.8E-13 7.7E-15 5.9E-15
4.8E-08 2E-11 1.2E-13 7.4E-16 6.3E-16 90cm
2.6E-07 5.1E-11 2E-13 1.5E-15 1.2E-15
2.3E-08 5.9E-12 2.4E-14 1.7E-16 1.1E-16 100cm 1.2E-07 1.5E-11 4.9E-14 4.1E-16 2E-16
1.1E-08 1.8E-12 5.5E-15 3.8E-17 2.5E-17 110cm
6E-08 4.7E-12 1.4E-14 1E-16 5.7E-17
5.4E-09 5.4E-13 1.5E-15 9.9E-18 8.6E-18 120cm 2.9E-08 1.5E-12 4.5E-15 2.6E-17 2.6E-17
2.6E-09 1.7E-13 4.8E-16 3E-18 3.4E-18 130cm 1.4E-08 4.6E-13 1.6E-15 8.9E-18 9.1E-18
1.3E-09 5.3E-14 1.7E-16 7.5E-19 1.6E-18 140cm
7E-09 1.5E-13 6.1E-16 1.9E-18 5.7E-18
Fluence N/cm^2/pri
Dose Equivalent
Fluence N/cm^2/pri
Dose Equivalent
Fluence N/cm^2/pri
Dose Equivalent
50
pSv/pri
pSv/pri
pSv/pri
150cm
6.2E-10 1.7E-14 6.4E-17 2.3E-19 6.4E-19 150cm
6MV
30x30cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
1.1E-05 1.3E-06 9.4E-07 2.1E-07 2.3E-07 0cm
8.9E-05 3E-06 1.2E-06 1.5E-07 1.5E-07
9.2E-06 4.8E-07 2.4E-07 1.5E-08 1.5E-08 10cm
5.3E-05 1.1E-06 2.9E-07 1.2E-08 1E-08
4.8E-06 1.3E-07 3.9E-08 1E-09 8.6E-10 20cm
2.6E-05 3.1E-07 4.9E-08 8.3E-10 6.8E-10
2.4E-06 3.7E-08 6E-09 7.8E-11 6.2E-11 30cm
1.3E-05 8.9E-08 7.6E-09 7.1E-11 5.6E-11
1.1E-06 1E-08 9.2E-10 7.1E-12 5.7E-12 40cm
6E-06 2.6E-08 1.2E-09 7.2E-12 5.9E-12
5.3E-07 3E-09 1.4E-10 7.7E-13 6.2E-13 50cm
2.8E-06 7.4E-09 1.8E-10 8.9E-13 7.2E-13
2.5E-07 8.6E-10 2.2E-11 9.8E-14 8.5E-14 60cm
1.3E-06 2.2E-09 2.9E-11 1.3E-13 1.1E-13
1.2E-07 2.5E-10 3.5E-12 1.6E-14 1.5E-14 70cm
6.4E-07 6.5E-10 4.8E-12 2.4E-14 2E-14
5.7E-08 7.4E-11 5.8E-13 2.8E-15 2.3E-15 80cm
3.1E-07 1.9E-10 8.7E-13 5.2E-15 3.5E-15
2.7E-08 2.2E-11 1E-13 5.5E-16 3.4E-16 90cm
1.5E-07 5.9E-11 1.7E-13 1.3E-15 6E-16
1.3E-08 6.8E-12 2E-14 1.7E-16 9E-17 100cm 7.1E-08 1.8E-11 4E-14 3.6E-16 1.6E-16
6.3E-09 2.1E-12 4.7E-15 3.6E-17 2.4E-17 110cm 3.4E-08 5.7E-12 1.1E-14 8.3E-17 3.7E-17
3E-09 6.5E-13 1.3E-15 1.1E-17 3.2E-18 120cm 1.7E-08 1.8E-12 3.5E-15 2.5E-17 7.2E-18
1.5E-09 2E-13 3.8E-16 1.9E-18 6.3E-19 130cm 8.1E-09 5.8E-13 1.2E-15 4.4E-18 1.2E-18
7.1E-10 6.5E-14 1.3E-16 7.2E-19 2.5E-19 140cm
4E-09 1.9E-13 4.1E-16 1.5E-18 5.3E-19
3.5E-10 2.1E-14 4.5E-17 1E-19 6.2E-20 150cm 1.9E-09 6.2E-14 1.5E-16 2.1E-19 1.4E-19
6MV
40x40cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
7.8E-06 1.2E-06 8.4E-07 1.8E-07 1.9E-07 0cm
6.2E-05 2.9E-06 1.1E-06 1.3E-07 1.3E-07
6.4E-06 4.7E-07 2.1E-07 1.3E-08 1.2E-08 10cm
3.7E-05 1E-06 2.7E-07 9.6E-09 8.9E-09
3.4E-06 1.3E-07 3.5E-08 8.4E-10 7.3E-10 20cm
1.8E-05 3E-07 4.4E-08 6.9E-10 5.7E-10
1.6E-06 3.6E-08 5.4E-09 6.4E-11 5.2E-11 30cm
8.7E-06 8.7E-08 6.8E-09 5.7E-11 4.6E-11
7.7E-07 1E-08 8.3E-10 5.7E-12 4.7E-12 40cm
4.1E-06 2.5E-08 1.1E-09 5.7E-12 4.9E-12
3.7E-07 2.9E-09 1.3E-10 6E-13 5.4E-13 50cm
1.9E-06 7.4E-09 1.6E-10 6.9E-13 6.4E-13
1.7E-07 8.5E-10 1.9E-11 7.7E-14 7.5E-14 60cm
9.2E-07 2.2E-09 2.5E-11 1.1E-13 9.5E-14
8.2E-08 2.5E-10 3.1E-12 1.2E-14 1.2E-14 70cm
4.4E-07 6.6E-10 4.2E-12 1.9E-14 1.6E-14
3.9E-08 7.5E-11 5E-13 2.2E-15 1.8E-15 80cm
2.1E-07 2E-10 7.7E-13 4.3E-15 2.4E-15
1.9E-08 2.3E-11 9E-14 5.2E-16 3.7E-16 90cm
1E-07 6.1E-11 1.6E-13 1.2E-15 4.7E-16
8.8E-09 7E-12 1.8E-14 1.2E-16 6E-17 100cm 4.8E-08 1.9E-11 3.7E-14 2.7E-16 6.2E-17
4.3E-09 2.2E-12 4.2E-15 3.3E-17 5.2E-18 110cm 2.3E-08 6.1E-12 1E-14 9E-17 7.7E-18
2.1E-09 6.8E-13 1.1E-15 1.3E-17 1.1E-18 120cm 1.1E-08 1.9E-12 3.3E-15 3.2E-17 1.5E-18
1E-09 2.2E-13 3.7E-16 3.9E-18 2E-19 130cm 5.5E-09 6.3E-13 1.2E-15 1.1E-17 4.7E-19
4.8E-10 7E-14 1.3E-16 1.5E-18 2.6E-19 140cm 2.7E-09 2E-13 4.2E-16 3.6E-18 3.6E-19
2.4E-10 2.3E-14 4.4E-17 2.2E-19 1.1E-20 150cm 1.3E-09 6.8E-14 1.5E-16 7.1E-19 1.4E-20
10MV
4x4cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
2.3E-05 1.2E-06 8.9E-07 2.3E-07 2.3E-07 0cm
0.00024 3.7E-06 1.3E-06 1.8E-07 1.6E-07
2.3E-05 5E-07 2.5E-07 2.2E-08 1.8E-08 10cm
0.00018 1.3E-06 3.4E-07 1.9E-08 1.4E-08
1.4E-05 1.6E-07 4.5E-08 1.9E-09 1.3E-09 20cm
0.0001 4E-07 6.1E-08 1.8E-09 1.2E-09
8E-06 4.8E-08 7.6E-09 1.8E-10 1.2E-10 30cm
5.6E-05 1.2E-07 1E-08 1.9E-10 1.3E-10
4.3E-06 1.4E-08 1.3E-09 2.1E-11 1.4E-11 40cm
3E-05 3.8E-08 1.8E-09 2.5E-11 1.8E-11
2.3E-06 4.4E-09 2.1E-10 3E-12 2.2E-12 50cm
1.6E-05 1.2E-08 3.1E-10 4.1E-12 3.1E-12
1.2E-06 1.3E-09 3.7E-11 4.4E-13 3.4E-13 60cm
8.5E-06 3.6E-09 5.8E-11 7.8E-13 5.9E-13
6.6E-07 4.1E-10 6.8E-12 8.6E-14 6.8E-14 70cm
4.5E-06 1.1E-09 1.2E-11 1.9E-13 1.4E-13
3.5E-07 1.3E-10 1.4E-12 1.9E-14 1.6E-14 80cm
2.4E-06 3.5E-10 3.1E-12 5E-14 4.1E-14
1.9E-07 4E-11 3.4E-13 5.4E-15 4.5E-15 90cm
1.3E-06 1.1E-10 9.5E-13 1.6E-14 1.3E-14
1E-07 1.3E-11 9.9E-14 1.7E-15 1.4E-15 100cm 6.9E-07 3.7E-11 3.3E-13 5.7E-15 4.7E-15
5.3E-08 4.1E-12 3.3E-14 6E-16 5.7E-16 110cm 3.7E-07 1.2E-11 1.3E-13 2E-15 1.8E-15
2.8E-08 1.4E-12 1.3E-14 1.8E-16 1.9E-16 120cm
2E-07 4.3E-12 5.3E-14 6.7E-16 6.9E-16
1.5E-08 4.6E-13 5E-15 7.1E-17 6.7E-17 130cm 1.1E-07 1.5E-12 2.3E-14 2.8E-16 2.7E-16
8.2E-09 1.6E-13 2.1E-15 3.1E-17 2.9E-17 140cm 5.8E-08 5.5E-13 9.8E-15 1.1E-16 1.1E-16
4.4E-09 5.8E-14 9.3E-16 1.1E-17 1.1E-17 150cm 3.2E-08 2.1E-13 4.5E-15 4E-17 4.6E-17
Fluence N/cm^2/pri
3.4E-09 4.8E-14 2.4E-16 5.8E-19 2.5E-18
Dose Equivalent
Fluence N/cm^2/pri
Dose Equivalent
Fluence N/cm^2/pri
Dose Equivalent
51
pSv/pri
pSv/pri
pSv/pri
10MV
10x10cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
2.3E-05 1.2E-06 9E-07 2.3E-07 2.3E-07 0cm
0.00023 3.6E-06 1.3E-06 1.8E-07 1.6E-07
2.3E-05 5E-07 2.5E-07 2.1E-08 1.8E-08 10cm
0.00018 1.3E-06 3.4E-07 1.8E-08 1.4E-08
1.4E-05 1.5E-07 4.4E-08 1.8E-09 1.3E-09 20cm
0.0001 3.9E-07 6E-08 1.7E-09 1.2E-09
7.8E-06 4.6E-08 7.6E-09 1.7E-10 1.2E-10 30cm
5.4E-05 1.2E-07 1E-08 1.9E-10 1.3E-10
4.2E-06 1.4E-08 1.3E-09 2E-11 1.4E-11 40cm
2.9E-05 3.7E-08 1.7E-09 2.5E-11 1.9E-11
2.3E-06 4.2E-09 2.1E-10 2.7E-12 2.2E-12 50cm
1.5E-05 1.1E-08 3E-10 4E-12 3.8E-12
1.2E-06 1.3E-09 3.6E-11 4.4E-13 4.3E-13 60cm
8.2E-06 3.4E-09 5.8E-11 7.9E-13 9.5E-13
6.4E-07 3.9E-10 6.7E-12 8.5E-14 1.1E-13 70cm
4.4E-06 1.1E-09 1.2E-11 2E-13 3E-13
3.4E-07 1.2E-10 1.4E-12 1.9E-14 3.2E-14 80cm
2.3E-06 3.4E-10 3.2E-12 5.2E-14 1E-13
1.8E-07 3.8E-11 3.5E-13 5.5E-15 1.2E-14 90cm
1.2E-06 1.1E-10 9.9E-13 1.6E-14 3.9E-14
9.6E-08 1.2E-11 1E-13 1.7E-15 4.1E-15 100cm 6.6E-07 3.6E-11 3.6E-13 6.1E-15 1.5E-14
5.1E-08 3.9E-12 3.6E-14 5.6E-16 1.6E-15 110cm 3.6E-07 1.2E-11 1.4E-13 2.2E-15 6E-15
2.7E-08 1.3E-12 1.4E-14 1.9E-16 6.2E-16 120cm 1.9E-07 4.1E-12 5.8E-14 7.3E-16 2.3E-15
1.5E-08 4.4E-13 5.6E-15 8.1E-17 2.5E-16 130cm
1E-07 1.4E-12 2.6E-14 2.8E-16 9.4E-16
7.8E-09 1.5E-13 2.4E-15 2.2E-17 9.6E-17 140cm 5.6E-08 5.2E-13 1.1E-14 9.2E-17 3.7E-16
4.2E-09 5.5E-14 1E-15 7.3E-18 3.8E-17 150cm
3E-08 2E-13 5.3E-15 2.9E-17 1.5E-16
Fluence N/cm^2/pri
Dose Equivalent
10MV
20x20cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
2.4E-05 1.3E-06 8.9E-07 2.2E-07 2.2E-07 0cm
0.00023 3.7E-06 1.3E-06 1.7E-07 1.6E-07
2.3E-05 5.1E-07 2.4E-07 2E-08 1.8E-08 10cm
0.00018 1.3E-06 3.3E-07 1.7E-08 1.4E-08
1.4E-05 1.6E-07 4.4E-08 1.7E-09 1.4E-09 20cm
9.8E-05 4E-07 5.9E-08 1.6E-09 1.3E-09
7.5E-06 4.7E-08 7.5E-09 1.7E-10 1.3E-10 30cm
5.2E-05 1.2E-07 1E-08 1.8E-10 1.4E-10
4E-06 1.4E-08 1.2E-09 1.9E-11 1.6E-11 40cm
2.8E-05 3.8E-08 1.7E-09 2.3E-11 2E-11
2.1E-06 4.4E-09 2.1E-10 2.6E-12 2.3E-12 50cm
1.5E-05 1.2E-08 3E-10 3.5E-12 3.3E-12
1.1E-06 1.3E-09 3.5E-11 4E-13 3.9E-13 60cm
7.8E-06 3.7E-09 5.4E-11 6.5E-13 6.5E-13
5.9E-07 4.2E-10 6.4E-12 7.3E-14 7.7E-14 70cm
4.1E-06 1.2E-09 1.1E-11 1.5E-13 1.4E-13
3.1E-07 1.3E-10 1.3E-12 1.6E-14 1.7E-14 80cm
2.2E-06 3.7E-10 2.9E-12 3.9E-14 3.5E-14
1.6E-07 4.2E-11 3.2E-13 4.3E-15 3.6E-15 90cm
1.2E-06 1.2E-10 8.6E-13 1.2E-14 9.2E-15
8.8E-08 1.3E-11 9.4E-14 1.2E-15 9.8E-16 100cm 6.2E-07 4E-11 3E-13 3.9E-15 2.7E-15
4.7E-08 4.4E-12 3E-14 4.1E-16 3.1E-16 110cm 3.3E-07 1.4E-11 1.1E-13 1.4E-15 8.9E-16
2.5E-08 1.5E-12 1.1E-14 1.4E-16 9.8E-17 120cm 1.8E-07 4.7E-12 4.6E-14 5.1E-16 3.1E-16
1.3E-08 5.1E-13 4.5E-15 5.5E-17 4.9E-17 130cm 9.6E-08 1.6E-12 1.9E-14 1.9E-16 1.4E-16
7.1E-09 1.8E-13 1.9E-15 1.8E-17 1.6E-17 140cm 5.2E-08 6E-13 8.3E-15 6.5E-17 4.8E-17
3.8E-09 6.3E-14 8E-16 5.6E-18 5.4E-18 150cm 2.8E-08 2.2E-13 3.6E-15 2E-17 1.6E-17
10MV
30x30cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
1.6E-05 1.2E-06 8.1E-07 1.8E-07 1.9E-07 0cm
0.00016 3.9E-06 1.2E-06 1.4E-07 1.3E-07
1.5E-05 5.2E-07 2.3E-07 1.6E-08 1.5E-08 10cm
0.00012 1.3E-06 3.1E-07 1.4E-08 1.2E-08
8.9E-06 1.6E-07 4.2E-08 1.3E-09 1.1E-09 20cm
6.4E-05 4.2E-07 5.6E-08 1.2E-09 9.8E-10
4.8E-06 4.9E-08 7E-09 1.2E-10 1E-10 30cm
3.4E-05 1.3E-07 9.5E-09 1.3E-10 1E-10
2.6E-06 1.5E-08 1.2E-09 1.4E-11 1.2E-11 40cm
1.8E-05 4.1E-08 1.6E-09 1.6E-11 1.4E-11
1.3E-06 4.6E-09 1.9E-10 1.8E-12 1.5E-12 50cm
9.4E-06 1.3E-08 2.7E-10 2.4E-12 2.1E-12
7E-07 1.4E-09 3.3E-11 2.7E-13 2.5E-13 60cm
4.9E-06 4.1E-09 5.1E-11 4.3E-13 4E-13
3.7E-07 4.6E-10 6E-12 4.8E-14 4.3E-14 70cm
2.6E-06 1.3E-09 1.1E-11 8.7E-14 7.9E-14
2E-07 1.5E-10 1.2E-12 8.7E-15 1.1E-14 80cm
1.4E-06 4.3E-10 2.7E-12 1.9E-14 2.2E-14
1E-07 4.8E-11 3.1E-13 2.2E-15 2.7E-15 90cm
7.3E-07 1.4E-10 8.6E-13 5.4E-15 6.4E-15
5.5E-08 1.6E-11 8.8E-14 6.8E-16 7.1E-16 100cm 3.9E-07 4.8E-11 3.1E-13 1.5E-15 1.6E-15
2.9E-08 5.3E-12 3.1E-14 1.5E-16 2.4E-16 110cm 2.1E-07 1.7E-11 1.2E-13 3.9E-16 5.2E-16
1.5E-08 1.8E-12 1.2E-14 5.2E-17 3.7E-17 120cm 1.1E-07 5.8E-12 4.9E-14 1.3E-16 1.2E-16
8.3E-09 6.3E-13 4.8E-15 1.4E-17 1.9E-17 130cm
6E-08 2.1E-12 2.2E-14 4E-17 5.1E-17
4.4E-09 2.2E-13 2.1E-15 4.1E-18 4.5E-18 140cm 3.2E-08 7.4E-13 9.7E-15 1.3E-17 1.4E-17
2.4E-09 8E-14 9.2E-16 1.5E-18 1.1E-18 150cm 1.7E-08 2.7E-13 4.4E-15 3.9E-18 2.3E-18
Fluence N/cm^2/pri
Dose Equivalent
Fluence N/cm^2/pri
Dose Equivalent
52
pSv/pri
pSv/pri
pSv/pri
10MV
40x40cm
Fluence N/cm^2/pri
Dose Equivalent
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
1.2E-05 1.2E-06 7.3E-07 1.5E-07 1.6E-07 0cm
0.00012 4E-06 1.1E-06 1.2E-07 1.2E-07
1.1E-05 5E-07 2.1E-07 1.4E-08 1.3E-08 10cm
8.8E-05 1.3E-06 2.9E-07 1.1E-08 1E-08
6.7E-06 1.6E-07 3.8E-08 1.1E-09 9.4E-10 20cm
4.8E-05 4.1E-07 5.1E-08 1E-09 8.5E-10
3.6E-06 4.8E-08 6.5E-09 1E-10 8.7E-11 30cm
2.5E-05 1.3E-07 8.7E-09 1.1E-10 9.2E-11
1.9E-06 1.5E-08 1.1E-09 1.1E-11 1E-11 40cm
1.3E-05 4.1E-08 1.4E-09 1.4E-11 1.3E-11
1E-06 4.6E-09 1.7E-10 1.5E-12 1.5E-12 50cm
7E-06 1.3E-08 2.5E-10 2.1E-12 2.1E-12
5.2E-07 1.4E-09 2.9E-11 2.3E-13 2.4E-13 60cm
3.7E-06 4.1E-09 4.5E-11 4E-13 4.1E-13
2.7E-07 4.6E-10 5.4E-12 4.5E-14 5E-14 70cm
1.9E-06 1.3E-09 9.5E-12 9.6E-14 9.8E-14
1.4E-07 1.5E-10 1.1E-12 1E-14 1.2E-14 80cm
1E-06 4.5E-10 2.4E-12 2.6E-14 2.6E-14
7.6E-08 4.9E-11 2.7E-13 2.4E-15 3E-15 90cm
5.4E-07 1.5E-10 7.2E-13 7.3E-15 7.2E-15
4E-08 1.6E-11 7.7E-14 7.7E-16 7.5E-16 100cm 2.9E-07 5.1E-11 2.5E-13 2.4E-15 2.1E-15
2.1E-08 5.6E-12 2.6E-14 2.6E-16 2.3E-16 110cm 1.5E-07 1.8E-11 9.3E-14 7.9E-16 6.3E-16
1.1E-08 1.9E-12 9.6E-15 6.9E-17 7.2E-17 120cm 8.2E-08 6.2E-12 3.8E-14 2.1E-16 2.1E-16
6.1E-09 6.7E-13 3.8E-15 2E-17 2.3E-17 130cm 4.4E-08 2.2E-12 1.5E-14 6.3E-17 7.2E-17
3.2E-09 2.4E-13 1.5E-15 7.9E-18 7.6E-18 140cm 2.4E-08 8.2E-13 6.5E-15 2.4E-17 2.2E-17
1.7E-09 8.7E-14 6.4E-16 2.4E-18 2.3E-18 150cm 1.3E-08 3E-13 2.8E-15 7.7E-18 6.8E-18
25MV
4x4cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
3.1E-05 1.2E-06 7.8E-07 2.1E-07 2E-07 0cm
0.00039 5.6E-06 1.2E-06 1.9E-07 1.6E-07
3.5E-05 4.7E-07 2.2E-07 2.4E-08 1.9E-08 10cm
0.00044 1.3E-06 3.1E-07 2.4E-08 1.7E-08
2.4E-05 1.6E-07 4.1E-08 2.5E-09 1.7E-09 20cm
0.00027 4.5E-07 6.1E-08 2.9E-09 1.9E-09
1.5E-05 5.1E-08 7.6E-09 3.2E-10 2.1E-10 30cm
0.00016 1.5E-07 1.1E-08 4.2E-10 2.8E-10
9E-06 1.7E-08 1.4E-09 4.7E-11 3.1E-11 40cm
9.6E-05 5.2E-08 2.3E-09 7.2E-11 5.1E-11
5.3E-06 5.7E-09 2.7E-10 7.9E-12 5.7E-12 50cm
5.4E-05 1.8E-08 5.2E-10 1.6E-11 1.2E-11
3.1E-06 1.9E-09 5.7E-11 1.7E-12 1.3E-12 60cm
3.3E-05 6.1E-09 1.4E-10 4.2E-12 3.5E-12
1.8E-06 6.5E-10 1.5E-11 4.2E-13 3.7E-13 70cm
1.8E-05 2.2E-09 4.6E-11 1.3E-12 1.2E-12
1.1E-06 2.3E-10 4.5E-12 1.3E-13 1.2E-13 80cm
1.1E-05 8.1E-10 1.8E-11 4.7E-13 4.7E-13
6.2E-07 8.3E-11 1.7E-12 4.3E-14 4.9E-14 90cm
6.2E-06 3.1E-10 7.5E-12 1.7E-13 1.9E-13
3.6E-07 3.1E-11 6.7E-13 1.6E-14 1.9E-14 100cm 3.6E-06 1.2E-10 3.4E-12 6.8E-14 7.9E-14
2.1E-07 1.2E-11 2.9E-13 6.1E-15 8E-15 110cm 2.1E-06 5.1E-11 1.6E-12 2.7E-14 3.4E-14
1.2E-07 4.8E-12 1.3E-13 2.3E-15 3.4E-15 120cm 1.2E-06 2.2E-11 7.6E-13 1.1E-14 1.5E-14
7.2E-08 2E-12 6.3E-14 9.6E-16 1.5E-15 130cm 7.1E-07 1E-11 3.7E-13 4.1E-15 6.6E-15
4.2E-08 8.9E-13 3E-14 3.7E-16 6.8E-16 140cm 4.2E-07 4.7E-12 1.8E-13 1.6E-15 2.9E-15
2.5E-08 4E-13 1.5E-14 1.4E-16 3E-16 150cm 2.4E-07 2.2E-12 9.2E-14 5.9E-16 1.3E-15
25MV
10x10cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
3.1E-05 1.2E-06 7.9E-07 2.1E-07 2E-07 0cm
0.00038 5.5E-06 1.3E-06 1.9E-07 1.6E-07
3.5E-05 4.7E-07 2.2E-07 2.4E-08 1.9E-08 10cm
0.00044 1.3E-06 3.2E-07 2.4E-08 1.7E-08
2.4E-05 1.6E-07 4.2E-08 2.5E-09 1.8E-09 20cm
0.00026 4.5E-07 6.1E-08 2.9E-09 2E-09
1.5E-05 5.1E-08 7.6E-09 3.2E-10 2.2E-10 30cm
0.00016 1.5E-07 1.1E-08 4.1E-10 3E-10
9E-06 1.7E-08 1.4E-09 4.6E-11 3.3E-11 40cm
9.2E-05 5.1E-08 2.3E-09 7E-11 5.6E-11
5.3E-06 5.6E-09 2.7E-10 7.7E-12 6.2E-12 50cm
5.3E-05 1.7E-08 5.1E-10 1.5E-11 1.4E-11
3.1E-06 1.9E-09 5.7E-11 1.6E-12 1.4E-12 60cm
3.1E-05 6E-09 1.4E-10 4E-12 4.6E-12
1.8E-06 6.5E-10 1.5E-11 4E-13 4.3E-13 70cm
1.8E-05 2.2E-09 4.6E-11 1.2E-12 1.8E-12
1.1E-06 2.3E-10 4.6E-12 1.2E-13 1.7E-13 80cm
1E-05 7.9E-10 1.8E-11 4.4E-13 8E-13
6.1E-07 8.1E-11 1.7E-12 4E-14 7.2E-14 90cm
6.1E-06 3E-10 7.5E-12 1.7E-13 3.8E-13
3.6E-07 3E-11 6.8E-13 1.5E-14 3.5E-14 100cm 3.5E-06 1.2E-10 3.4E-12 6.7E-14 1.9E-13
2.1E-07 1.2E-11 3E-13 6E-15 1.6E-14 110cm 2.1E-06 4.9E-11 1.6E-12 2.9E-14 9.2E-14
1.2E-07 4.7E-12 1.4E-13 2.4E-15 7.9E-15 120cm 1.2E-06 2.1E-11 7.5E-13 1.2E-14 4.7E-14
7E-08 1.9E-12 6.3E-14 9.8E-16 4E-15 130cm
7E-07 9.6E-12 3.6E-13 5.2E-15 2.4E-14
4.1E-08 8.5E-13 3E-14 4.1E-16 2.1E-15 140cm 4.1E-07 4.5E-12 1.8E-13 2.4E-15 1.3E-14
2.4E-08 3.8E-13 1.5E-14 1.7E-16 1E-15 150cm 2.4E-07 2.1E-12 8.8E-14 9.3E-16 7.7E-15
Fluence N/cm^2/pri
Dose Equivalent
Fluence N/cm^2/pri
Dose Equivalent
53
pSv/pri
pSv/pri
pSv/pri
25MV
20x20cm
Fluence N/cm^2/pri
Dose Equivalent
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
3.1E-05 1.2E-06 7.8E-07 2E-07 1.9E-07 0cm
0.00037 5.7E-06 1.3E-06 1.8E-07 1.5E-07
3.4E-05 4.8E-07 2.2E-07 2.3E-08 1.9E-08 10cm
0.00042 1.3E-06 3.1E-07 2.2E-08 1.8E-08
2.3E-05 1.6E-07 4.1E-08 2.4E-09 1.9E-09 20cm
0.00026 4.6E-07 6E-08 2.7E-09 2.1E-09
1.4E-05 5.2E-08 7.5E-09 3E-10 2.4E-10 30cm
0.00015 1.6E-07 1.1E-08 3.9E-10 3.2E-10
8.4E-06 1.7E-08 1.4E-09 4.3E-11 3.7E-11 40cm
8.7E-05 5.4E-08 2.2E-09 6.4E-11 5.6E-11
5E-06 5.9E-09 2.6E-10 7.1E-12 6.6E-12 50cm
5E-05 1.8E-08 5E-10 1.4E-11 1.2E-11
2.9E-06 2E-09 5.6E-11 1.4E-12 1.4E-12 60cm
2.9E-05 6.5E-09 1.3E-10 3.6E-12 3.1E-12
1.7E-06 6.9E-10 1.4E-11 3.6E-13 3.3E-13 70cm
1.7E-05 2.3E-09 4.3E-11 1.2E-12 8.9E-13
9.6E-07 2.4E-10 4.3E-12 1.2E-13 9.9E-14 80cm
9.8E-06 8.6E-10 1.6E-11 4.7E-13 2.9E-13
5.6E-07 8.8E-11 1.6E-12 4.1E-14 3.3E-14 90cm
5.7E-06 3.3E-10 6.8E-12 2E-13 1E-13
3.3E-07 3.3E-11 6.2E-13 1.5E-14 1.1E-14 100cm 3.3E-06 1.3E-10 3E-12 8.7E-14 3.7E-14
1.9E-07 1.3E-11 2.7E-13 6.4E-15 3.9E-15 110cm 1.9E-06 5.3E-11 1.4E-12 3.7E-14 1.3E-14
1.1E-07 5.1E-12 1.2E-13 2.6E-15 1.4E-15 120cm 1.1E-06 2.3E-11 6.5E-13 1.5E-14 5E-15
6.3E-08 2.1E-12 5.6E-14 1.1E-15 5.6E-16 130cm 6.5E-07 1E-11 3.1E-13 6.9E-15 2.1E-15
3.7E-08 9E-13 2.6E-14 5E-16 2E-16 140cm 3.8E-07 4.6E-12 1.5E-13 2.8E-15 7.7E-16
2.2E-08 4E-13 1.3E-14 2E-16 8.1E-17 150cm 2.2E-07 2.2E-12 7.4E-14 1.1E-15 3.1E-16
25MV
30x30cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
2E-05 1.1E-06 7E-07 1.6E-07 1.6E-07 0cm
0.00025 6.4E-06 1.2E-06 1.4E-07 1.2E-07
2.1E-05 4.8E-07 2E-07 1.7E-08 1.5E-08 10cm
0.00027 1.4E-06 2.9E-07 1.6E-08 1.4E-08
1.4E-05 1.6E-07 3.9E-08 1.7E-09 1.4E-09 20cm
0.00016 4.8E-07 5.7E-08 1.9E-09 1.5E-09
8.6E-06 5.4E-08 7.1E-09 2E-10 1.7E-10 30cm
9.2E-05 1.7E-07 1.1E-08 2.6E-10 2.2E-10
5.1E-06 1.8E-08 1.3E-09 2.8E-11 2.6E-11 40cm
5.3E-05 5.7E-08 2.1E-09 4.3E-11 4E-11
3E-06 6.2E-09 2.4E-10 4.6E-12 4.7E-12 50cm
3.1E-05 2E-08 4.4E-10 8.8E-12 8.7E-12
1.7E-06 2.2E-09 5E-11 9.2E-13 1E-12 60cm
1.8E-05 7.2E-09 1.2E-10 2.4E-12 2.2E-12
9.9E-07 7.6E-10 1.2E-11 2.2E-13 2.5E-13 70cm
1E-05 2.6E-09 3.6E-11 7.3E-13 6.5E-13
5.7E-07 2.7E-10 3.7E-12 7E-14 6.9E-14 80cm
5.9E-06 9.7E-10 1.4E-11 3E-13 2.1E-13
3.3E-07 1E-10 1.3E-12 2.4E-14 2.4E-14 90cm
3.4E-06 3.7E-10 5.6E-12 1.2E-13 7.4E-14
1.9E-07 3.8E-11 5.2E-13 9E-15 8.3E-15 100cm
2E-06 1.5E-10 2.6E-12 4.9E-14 2.7E-14
1.1E-07 1.5E-11 2.2E-13 3.8E-15 2.9E-15 110cm 1.1E-06 6E-11 1.1E-12 1.9E-14 9.9E-15
6.4E-08 5.8E-12 1E-13 1.6E-15 1.1E-15 120cm 6.6E-07 2.5E-11 5.3E-13 8.9E-15 3.7E-15
3.7E-08 2.4E-12 4.6E-14 6.6E-16 4.1E-16 130cm 3.8E-07 1.1E-11 2.5E-13 3.6E-15 1.4E-15
2.2E-08 1E-12 2.2E-14 3.1E-16 1.5E-16 140cm 2.2E-07 4.9E-12 1.2E-13 1.8E-15 5.3E-16
1.3E-08 4.4E-13 1E-14 1.3E-16 5.8E-17 150cm 1.3E-07 2.3E-12 6.1E-14 8E-16 2E-16
25MV
40x40cm
0cm
10cm
20cm
30cm
40cm
50cm
60cm
70cm
80cm
90cm
100cm
110cm
120cm
130cm
140cm
150cm
0-10
40-50 85-95 130-140 170-180
0-10
40-50 85-95 130-140 170-180
1.5E-05 1E-06 6.3E-07 1.3E-07 1.4E-07 0cm
0.00019 7.4E-06 1.2E-06 1.2E-07 1.1E-07
1.5E-05 4.6E-07 1.8E-07 1.4E-08 1.3E-08 10cm
0.00019 1.3E-06 2.7E-07 1.3E-08 1.1E-08
1E-05 1.6E-07 3.6E-08 1.4E-09 1.2E-09 20cm
0.00011 4.7E-07 5.2E-08 1.5E-09 1.2E-09
6.1E-06 5.2E-08 6.5E-09 1.6E-10 1.4E-10 30cm
6.5E-05 1.6E-07 9.6E-09 2E-10 1.7E-10
3.6E-06 1.8E-08 1.2E-09 2.2E-11 2E-11 40cm
3.8E-05 5.7E-08 1.9E-09 3.1E-11 3E-11
2.1E-06 6.1E-09 2.2E-10 3.4E-12 3.6E-12 50cm
2.2E-05 2E-08 4E-10 5.9E-12 6.2E-12
1.2E-06 2.1E-09 4.5E-11 6.2E-13 7E-13 60cm
1.3E-05 7.2E-09 1E-10 1.4E-12 1.6E-12
7E-07 7.6E-10 1.1E-11 1.4E-13 1.8E-13 70cm
7.2E-06 2.6E-09 3.2E-11 3.9E-13 5.2E-13
4E-07 2.7E-10 3.2E-12 4E-14 5.2E-14 80cm
4.1E-06 9.8E-10 1.2E-11 1.4E-13 1.6E-13
2.3E-07 1E-10 1.1E-12 1.3E-14 1.7E-14 90cm
2.6E-06 3.8E-10 5.1E-12 5.3E-14 6.8E-14
1.3E-07 3.8E-11 4.6E-13 4.2E-15 6.1E-15 100cm 1.4E-06 1.5E-10 2.2E-12 1.6E-14 2.6E-14
7.9E-08 1.5E-11 2E-13 1.6E-15 2.7E-15 110cm 8.2E-07 6E-11 1E-12 6E-15 1.1E-14
4.5E-08 5.8E-12 9E-14 5.7E-16 1E-15 120cm 4.7E-07 2.5E-11 4.9E-13 2.5E-15 4.6E-15
2.6E-08 2.4E-12 4.1E-14 2.2E-16 4.5E-16 130cm 2.7E-07 1.1E-11 2.3E-13 8.9E-16 2.2E-15
1.5E-08 1E-12 2E-14 7.9E-17 2.1E-16 140cm 1.6E-07 4.8E-12 1.1E-13 3.4E-16 1.1E-15
8.9E-09 4.3E-13 9.5E-15 3E-17 8.9E-17 150cm 9.2E-08 2.2E-12 5.7E-14 1.3E-16 5.3E-16
Fluence N/cm^2/pri
Dose Equivalent
Fluence N/cm^2/pri
Dose Equivalent
54
pSv/pri
pSv/pri
pSv/pri
Figure 4-2a The Fluence and Ambient Dose Equivalent behind the wall with different thicknesses and scattering angles for 6MV beam
55
Figure 4-2b The Fluence and Ambient Dose Equivalent behind the wall with different thicknesses and scattering angles for 10MV beam
56
Figure 4-2c The Fluence and Ambient Dose Equivalent behind the wall with different thicknesses and scattering angles for 25MV beam
57
Table 4-2 The Tenth Value Layers (TVL) for patient-scattered radiations for different beam
energy, field size and scattering angle
4cmx4cm 10cmx10cm 20cmx20cm 30cmx30cm 40cmx40cm NCRP151
6MV
0-10 deg
114.86
113.74
109.92
105.69
104.35
40-50 deg
51.69
51.10
50.95
51.31
51.77
85-95 deg
37.63
37.37
37.28
37.55
37.73
130-140 deg
22.14
21.98
21.92
21.56
21.44
170-180 deg
20.79
20.68
20.78
20.68
20.73
54.05
39.95
35.25
10MV
4cmx4cm 10cmx10cm 20cmx20cm 30cmx30cm 40cmx40cm NCRP151
0-10 deg 132.79
131.87
128.60
124.73
123.46
40-50 deg
58.75
55.90
55.37
55.44
56.41
56.94
85-95 deg
42.3
39.82
39.57
39.63
40.11
40.33
130-140 deg
35.25
24.19
23.93
24.07
23.59
23.52
170-180 deg
22.49
22.35
22.62
22.55
22.62
25MV
4cmx4cm 10cmx10cm 20cmx20cm 30cmx30cm 40cmx40cm NCRP151
0-10 deg 162.72
161.78
157.78
153.32
152.00
40-50 deg
68.15
57.76
57.29
57.76
59.43
60.18
85-95 deg
44.65
40.42
40.22
40.39
41.06
41.42
130-140 deg
37.6
26.22
26.13
26.17
25.37
25.04
170-180 deg
24.00
24.06
24.50
24.15
23.91
58
4.4 References
[1] FLUKA Online manual, http://www.fluka.org/fluka.php?id=man_onl
[2] S. Agosteo, M. Magistris, A. Mereghetti, M. Silari, Z. Zajacova, “Shielding
data for 100–250 MeV proton accelerators: Double differential neutron
distributions and attenuation in concrete”, Nuclear Instruments and Methods in
Physics Research. Section B, Beam Interactions with Materials and Atoms, 2007
[3] Shultis JK, Faw RE, “Radiation shielding”, Upper Saddle River: Prentice Hall
PTR, 1996
[4] S. Agosteo, M. Magistris, A. Mereghetti, M. Silari, Z. Zajacova, “Shielding
data for 100–250 MeV proton accelerators: Attenuation of secondary radiation in
thick iron and concrete/iron shields”, Nuclear Instruments and Methods in Physics
Research. Section B, Beam Interactions with Materials and Atoms, 2008
[5] Peter J. Biggs, “Obliquity factors for 60 Co and 4, 10, and 18 MV x rays for
concrete, steel, and lead and angles of incidence between 0 and 70 degrees”,
Health Physics, 1996
[6] M. Pelliccioni, “Overview of fluence-to-effective dose and fluence-to-ambient
dose equivalent conversion coefficients for high energy radiation calculated using
FLUKA code”, Radiation Protection Dosimetry, 2000
[7] Morgan, H., “NCRP Report 151 Structural shielding design and evaluation for
megavoltage x-and gamma-ray radiotherapy facilities”, Journal of Radiological
Protection, 2006
[8] Peter J. Biggs and John R. Styczynski, “Do angles of obliquity apply to 30
degrees scattered radiation from megavoltage beams?”, Health Physics, 2008
59
Chapter 5:
Conclusion
Shielding design for a radiotherapy treatment room is a complicated and
important task for hospital administrator who plan to install a new linear
accelerator. The local regulations limit the dose received by individuals outside
the treatment room and the shielding design must fulfil the requirements in the
regulations. Various sources of radiations must be taken into account, which
include the primary beam from the linear accelerator, the leakage radiation from
the gantry and the scattered radiation from the patient and other objects in
addition to the primary beam.
In this dissertation, we focused on the scattered radiation from the patient.
The objective is to have better understanding of the scatters when designing the
shielding of a treatment room. By modelling the patient with a sphere of ICRP
soft tissue, we analysed the characteristics of the scattered radiation, which
include the angular distributions of the scattered particles and their energy
spectrum. It was found that both the number of scatter particles and energy of the
scatter particles increase with increasing primary beam energy and decreasing
scatter angle.
In addition to the characteristics of the scattered radiation, it is important
to know how much the concrete attenuates the scattered radiation, so that the
thickness of the wall required to fulfil the dose limits in the local regulations can
be estimated. We performed Monte Carlo simulations to collect the transmission
60
data of scattered particles passing through the concrete walls of different thickness
in different directions. The properties of the collected transmission data can be
explained by the characteristics of the scattered radiation. The concrete is more
effective in attenuating the backscatters than the forward scatters because of the
low energy of the backscatters.
The collected data, in tabular form, which includes the dose calibration
results, scatter yields and the transmission data of the scatters in concrete, can be
directly used to estimate the scattered dose outside a designated treatment room
for a particular beam energy and field size.
In this dissertation, we limit ourselves in studying the Elekta Precise linear
accelerator and the concrete commonly used in Hong Kong. The same approach
can be applied for other models of linear accelerators and other compositions of
concrete. It is worth to study other linear accelerators and also different
compositions of concrete and by comparing the results, more generalised
conclusions or formalisms can be derived.
61
Appendix A:
FLUKA Source Code
A.1: User Routine source.f for Reading IAEA phase
space files
*$ CREATE SOURCE.FOR
*COPY SOURCE
*
*=== source ===========================================================*
*
#ifdef DOUBLE
#define IAEA_Float real*8
#else
#define IAEA_Float real*4
#endif
#define IAEA_I16 integer*2
#define IAEA_I32 integer*4
#define IAEA_I64 integer*8
#define NUM_EXTRA_LONG 1
#define NUM_EXTRA_FLOAT 2
#define NUM_FILE 4
#define FILENAME1 '/IAEAphasespace/ELEKTA_PRECISE_10mv_part3'
#define FILENAME2 '/IAEAphasespace/ELEKTA_PRECISE_10mv_part1'
#define FILENAME3 '/IAEAphasespace/ELEKTA_PRECISE_10mv_part2'
#define FILENAME4 '/IAEAphasespace/ELEKTA_PRECISE_10mv_part4'
#define FILENAME5 ''
#define FILENAME6 ''
#define FILENAME7 ''
#define FILENAME8 ''
#define FILENAME9 ''
#define FILENAME10 ''
SUBROUTINE SOURCE ( NOMORE )
INCLUDE '(DBLPRC)'
INCLUDE '(DIMPAR)'
INCLUDE '(IOUNIT)'
INCLUDE '(CASLIM)'
*
*----------------------------------------------------------------------*
*
*
*
Copyright (C) 1990-2010
by Alfredo Ferrari & Paola Sala *
62
*
All Rights Reserved.
*
*
*
*
*
*
New source for FLUKA9x-FLUKA20xy:
*
*
*
Created on 07 January 1990 by Alfredo Ferrari & Paola Sala *
*
Infn - Milan
*
*
*
*
*
Last change on 17-Oct-10 by Alfredo Ferrari
*
*
*
* This is just an example of a possible user written source routine. *
* note that the beam card still has some meaning - in the scoring the *
* maximum momentum used in deciding the binning is taken from the
* beam momentum. Other beam card parameters are obsolete.
*
*
*
*
*
Output variables:
*
*
*
*
Nomore = if > 0 the run will be terminated
*
*
*
*----------------------------------------------------------------------*
*
INCLUDE '(BEAMCM)'
INCLUDE '(FHEAVY)'
INCLUDE '(FLKSTK)'
INCLUDE '(IOIOCM)'
INCLUDE '(LTCLCM)'
INCLUDE '(PAPROP)'
INCLUDE '(SOURCM)'
INCLUDE '(SUMCOU)'
*
LOGICAL LFIRST
SAVE LFIRST
DATA LFIRST / .TRUE. /
character*80 file_name(1:10)
character*80 phasespacebuf
integer*4 i
IAEA_I32 source_read(1:10),source_write,access_read,access_write,
&
source_readps, result
parameter
(access_read=1,access_write=2)
IAEA_I32
&
extra_ints(NUM_EXTRA_LONG),n_stat,
iextrafloat,iextralong,ind,extralong_type
IAEA_I64
histories(10),nphot,irecord,
& read_indep,nrecorded,norig
IAEA_Float, Dimension(:),Allocatable :: E, wt, x, y, z, u, v, w
IAEA_I32, Dimension(:),Allocatable :: typ
IAEA_Float
extra_floats(NUM_EXTRA_FLOAT)
IAEA_I32
typo
SAVE E, wt, x, y, z, u, v, w, typ, histories
SAVE source_readps, phasespacebuf
IAEA_Float SE,Swt,Sx,Sy,Sz,Su,Sv,Sw
IAEA_I32
Styp
IAEA_I64
histindex,sumhistindex
IAEA_I64
sumi
63
IAEA_I32, Dimension(:),Allocatable :: A, INDX
IAEA_I32, Dimension(:),Allocatable :: B
IAEA_I64
buffer
IAEA_I64
bufferi, tempiii, orghist, totalorghist
IAEA_Float
EQQQ
SAVE A, buffer, histindex
integer
data
FlukaParticle(1:5)
FlukaParticle/7,3,4,8,1/
*
*======================================================================*
*
*
*
BASIC VERSION
*
*
*
*======================================================================*
NOMORE = 0
* +-------------------------------------------------------------------*
* | First call initializations:
IF ( LFIRST ) THEN
* | *** The following 3 cards are mandatory ***
TKESUM = ZERZER
LFIRST = .FALSE.
LUSSRC = .TRUE.
* | *** User initialization ***
do i=1,len(phasespacebuf)
phasespacebuf(i:i) = char(0)
end do
WRITE(LUNOUT,*) 'SOURCE.F CALLED'
file_name(1) = FILENAME1
file_name(2) = FILENAME2
file_name(3) = FILENAME3
file_name(4) = FILENAME4
file_name(5) = FILENAME5
file_name(6) = FILENAME6
file_name(7) = FILENAME7
file_name(8) = FILENAME8
file_name(9) = FILENAME9
file_name(10) = FILENAME10
do i=1, NUM_FILE
call iaea_new_source(source_read(i),file_name(i)
& ,access_read,result)
if( result.lt.0 ) then
write(LUNERR,*)
& 'Error creating new source for reading particles '
64
& , result
call exit(1)
end if
end do
phasespacebuf = "TEMP"
call iaea_new_source(source_write,phasespacebuf,
& access_write,result)
if( result.lt.0 ) then
write(LUNERR,*) 'Error create new source write temp'
call flush(LUNERR)
call exit(1)
end if
iextrafloat = 0
iextralong = 0
call iaea_set_extra_numbers(source_write,iextrafloat,iextralong)
typo = -1 ! could be 0
sumhistories = 0
totalorghist = 0
do i=1, NUM_FILE
call iaea_get_max_particles(source_read(i), typo, histories(i))
histories(i) = histories(i) -1
sumhistories = sumhistories + histories(i)
call iaea_get_total_original_particles(source_read(i), orghist)
totalorghist = orghist + totalorghist
end do
write(LUNLOG,*) "totalorghist = ", totalorghist
call flush(LUNLOG)
write(LUNERR,*) 'Total number of particles in File: '
& ,sumhistories
buffer = Ncases
write(LUNERR,*) 'Total number of particles in RAM: ',buffer
call flush(LUNERR)
Allocate(A(1:buffer))
Allocate(INDX(1:buffer))
65
do i=1, buffer
A(i) = floor(FLRNDM(i) * (sumhistories))+1
end do
call SORTRX(buffer,A,INDX)
sumi = 1
bufferi = 1
do i=1, NUM_FILE
do irecord=1,histories(i)
call iaea_get_particle(source_read(i), n_stat,
&
Styp,SE,Swt,
&
Sx,Sy,Sz,Su,
&
Sv,Sw,extra_floats,extra_ints)
117
if (bufferi .lt. (buffer+1)) then
if (A(INDX(bufferi)) .eq. sumi) then
extra_floats(1) = 0
extra_floats(2) = 0
extra_ints(1) = 0
call iaea_write_particle(source_write,n_stat,Styp,SE,
&
Swt,Sx,Sy,Sz,
&
Su,Sv,Sw,extra_floats,extra_ints)
bufferi = bufferi + 1
go to 117
end if
end if
sumi = sumi + 1
if( n_stat.eq.-1 ) then
WRITE(LUNERR,*) 'Finished Reading File ',i
WRITE(LUNERR,*) histories(i), ' is expected'
WRITE(LUNERR,*) irecord, ' is read'
call flush(LUNERR)
exit ! i.e. end of file
end if
end do
end do
totalorghist = totalorghist * buffer / sumhistories
call iaea_set_total_original_particles(source_write,
& totalorghist)
call iaea_update_header(source_write, result)
call iaea_destroy_source(source_write, result)
do i=1, NUM_FILE
call iaea_destroy_source(source_read(i), result)
66
end do
call iaea_new_source(source_readps,phasespacebuf
& ,access_read,result)
if( result.lt.0 ) then
write(LUNERR,*)
& 'Error creating new source for reading PS file'
call flush(LUNERR)
call exit(1)
end if
WRITE(LUNERR,*) 'TOTAL Read: ', sumi
write(LUNERR,*) 'Finish READ'
call flush(LUNERR)
histindex = 0
END IF
histindex = histindex + 1
if ( histindex > buffer) then
histindex = 1
end if
call iaea_get_particle(source_readps, n_stat,
&
Styp,SE,Swt,
&
Sx,Sy,Sz,Su,
&
Sv,Sw,extra_floats,extra_ints)
* |
* +-------------------------------------------------------------------*
* Push one source particle to the stack. Note that you could as well
* push many but this way we reserve a maximum amount of space in the
* stack for the secondaries to be generated
* Npflka is the stack counter: of course any time source is called it
* must be =0
NPFLKA = NPFLKA + 1
* Wt is the weight of the particle
*
WTFLK (NPFLKA) = ONEONE
WTFLK (NPFLKA) = Swt
WEIPRI = WEIPRI + WTFLK (NPFLKA)
* Particle type (1=proton.....). Ijbeam is the type set by the BEAM
* card
* +-------------------------------------------------------------------*
67
IONID = FlukaParticle(Styp)
ILOFLK (NPFLKA) = IONID
* | Flag this is prompt radiation
LRADDC (NPFLKA) = .FALSE.
* | Group number for "low" energy neutrons, set to 0 anyway
IGROUP (NPFLKA) = 0
* |
* +-------------------------------------------------------------------*
* From this point .....
* Particle generation (1 for primaries)
LOFLK (NPFLKA) = 1
* User dependent flag:
LOUSE (NPFLKA) = 0
* No channeling:
LCHFLK (NPFLKA) = .FALSE.
DCHFLK (NPFLKA) = ZERZER
* User dependent spare variables:
DO 100 ISPR = 1, MKBMX1
SPAREK (ISPR,NPFLKA) = ZERZER
100 CONTINUE
* User dependent spare flags:
DO 200 ISPR = 1, MKBMX2
ISPARK (ISPR,NPFLKA) = 0
200 CONTINUE
* Save the track number of the stack particle:
ISPARK (MKBMX2,NPFLKA) = NPFLKA
NPARMA = NPARMA + 1
NUMPAR (NPFLKA) = NPARMA
NEVENT (NPFLKA) = 0
DFNEAR (NPFLKA) = +ZERZER
* ... to this point: don't change anything
* Particle age (s)
AGESTK (NPFLKA) = +ZERZER
AKNSHR (NPFLKA) = -TWOTWO
* Kinetic energy of the particle (GeV)
TKEFLK (NPFLKA) = SE/1000.0
* Particle momentum
PMOFLK (NPFLKA) = SQRT ( TKEFLK (NPFLKA) * ( TKEFLK (NPFLKA)
&
+ TWOTWO * AM (IONID) ) )
TXFLK (NPFLKA) = Su
TYFLK (NPFLKA) = Sv
if ((TXFLK(NPFLKA)**2+TYFLK(NPFLKA)**2).lt.ONEONE) then
TZFLK (NPFLKA) = SQRT ( ONEONE - TXFLK (NPFLKA)**2
&
- TYFLK (NPFLKA)**2 )
else
TXFLK (NPFLKA) = ONEONE
TYFLK (NPFLKA) = ZEROZERO
TZFLK (NPFLKA) = ZEROZERO
WEIPRI = WEIPRI - WTFLK (NPFLKA)
68
WTFLK (NPFLKA) = ZEROZERO
write(LUNERR,*) 'Bad cosines'
call flush(LUNERR)
end if
* Polarization cosines:
TXPOL (NPFLKA) = -TWOTWO
TYPOL (NPFLKA) = +ZERZER
TZPOL (NPFLKA) = +ZERZER
* Particle coordinates
XFLK (NPFLKA) = Sx
YFLK (NPFLKA) = Sy
ZFLK (NPFLKA) = Sz
* Calculate the total kinetic energy of the primaries: don't change
IF ( ILOFLK (NPFLKA) .EQ. -2 .OR. ILOFLK (NPFLKA) .GT. 100000 )
& THEN
TKESUM = TKESUM + TKEFLK (NPFLKA) * WTFLK (NPFLKA)
ELSE IF ( ILOFLK (NPFLKA) .NE. 0 ) THEN
TKESUM = TKESUM + ( TKEFLK (NPFLKA) + AMDISC (ILOFLK(NPFLKA)) )
&
* WTFLK (NPFLKA)
ELSE
TKESUM = TKESUM + TKEFLK (NPFLKA) * WTFLK (NPFLKA)
END IF
RADDLY (NPFLKA) = ZERZER
* Here we ask for the region number of the hitting point.
*
NREG (NPFLKA) = ...
* The following line makes the starting region search much more
* robust if particles are starting very close to a boundary:
CALL GEOCRS ( TXFLK (NPFLKA), TYFLK (NPFLKA), TZFLK (NPFLKA) )
CALL GEOREG ( XFLK (NPFLKA), YFLK (NPFLKA), ZFLK (NPFLKA),
&
NRGFLK(NPFLKA), IDISC )
* Do not change these cards:
CALL GEOHSM ( NHSPNT (NPFLKA), 1, -11, MLATTC )
NLATTC (NPFLKA) = MLATTC
CMPATH (NPFLKA) = ZERZER
CALL SOEVSV
RETURN
*=== End of subroutine Source =========================================*
END
69
A.2: User Routine mgdraw.f for Writing IAEA phase
space files
*$ CREATE MGDRAW.FOR
*COPY MGDRAW
*
*
*=== mgdraw ===========================================================*
*
#ifdef DOUBLE
#define IAEA_Float real*8
#else
#define IAEA_Float real*4
#endif
#define IAEA_I16 integer*2
#define IAEA_I32 integer*4
#define IAEA_I64 integer*8
#define NUM_EXTRA_LONG 1
#define NUM_EXTRA_FLOAT 1
#define REGFROMNAME "TARGET"
#define REGTONAME "VOID"
SUBROUTINE MGDRAW ( ICODE, MREG )
INCLUDE '(DBLPRC)'
INCLUDE '(DIMPAR)'
INCLUDE '(IOUNIT)'
*
*----------------------------------------------------------------------*
*
*
*
Copyright (C) 1990-2006
*
All Rights Reserved.
by
Alfredo Ferrari
*
*
*
*
*
MaGnetic field trajectory DRAWing: actually this entry manages *
*
all trajectory dumping for
*
drawing
*
Created on 01 march 1990 by
*
*
*
*
*
*
*
*
Alfredo Ferrari
INFN - Milan
Last change 05-may-06
*
by
Alfredo Ferrari
INFN - Milan
*
*
*
*
*
*
*----------------------------------------------------------------------*
*
INCLUDE '(CASLIM)'
INCLUDE '(COMPUT)'
INCLUDE '(SOURCM)'
70
INCLUDE '(FHEAVY)'
INCLUDE '(FLKSTK)'
INCLUDE '(GENSTK)'
INCLUDE '(MGDDCM)'
INCLUDE '(PAPROP)'
INCLUDE '(QUEMGD)'
INCLUDE '(SUMCOU)'
INCLUDE '(TRACKR)'
*
DIMENSION DTQUEN ( MXTRCK, MAXQMG )
*
SAVE REGFROM, REGTO
CHARACTER*20 FILNAM
LOGICAL LFCOPE
SAVE LFCOPE
DATA LFCOPE / .FALSE. /
LOGICAL FIRSTBOUND
SAVE FIRSTBOUND
DATA FIRSTBOUND / .TRUE. /
IAEA_I32
&
source_read,source_write,access_read,access_write,
result
IAEA_I32
&
typ,extra_ints(NUM_EXTRA_LONG),n_stat,
iextrafloat,iextralong,ind,extralong_type
parameter
(access_read=1,access_write=2)
IAEA_Float
&
E, wt, x, y, z, u, v, w, z_constant,
extra_floats(NUM_EXTRA_FLOAT)
IAEA_I64
histories,nphot,irecord,read_indep,nrecorded,norig
IAEA_I64
totalorghist
INTEGER IERR1, IERR2
integer
data
IAEAParticle(1:8)
IAEAParticle/5,-1,2,3,-1,-1,1,4/
CHARACTER*8 REGFROMNAMEs, REGTONAMEs
INTEGER REGFROMNUM, REGTONUM
SAVE REGFROMNUM, REGTONUM, totalorghist
*
*----------------------------------------------------------------------*
*
*
*
Icode = 1: call from Kaskad
*
Icode = 2: call from Emfsco
*
*
Icode = 3: call from Kasneu
*
*
Icode = 4: call from Kashea
*
*
Icode = 5: call from Kasoph
*
*
*
*
*----------------------------------------------------------------------*
*
*
* +-------------------------------------------------------------------*
* | Quenching is activated
IF ( LQEMGD ) THEN
IF ( MTRACK .GT. 0 ) THEN
RULLL = ZERZER
CALL QUENMG ( ICODE, MREG, RULLL, DTQUEN )
WRITE (IODRAW) ( ( SNGL (DTQUEN (I,JBK)), I = 1, MTRACK ),
71
&
JBK = 1, NQEMGD )
END IF
END IF
* | End of quenching
* +-------------------------------------------------------------------*
RETURN
*
*======================================================================*
*
*
*
Boundary-(X)crossing DRAWing:
*
*
*
*
*
*
*
*
*
*
*
*
*
Icode = 1x: call from Kaskad
*
19: boundary crossing
*
Icode = 2x: call from Emfsco
*
29: boundary crossing
*
Icode = 3x: call from Kasneu
*
39: boundary crossing
*
Icode = 4x: call from Kashea
*
49: boundary crossing
*
Icode = 5x: call from Kasoph
*
59: boundary crossing
*
*
*
*======================================================================*
*
*
ENTRY BXDRAW ( ICODE, MREG, NEWREG, XSCO, YSCO, ZSCO )
IF ( FIRSTBOUND ) THEN
FIRSTBOUND = .FALSE.
IF ( KOMPUT .EQ. 2 ) THEN
FILNAM = '/'//CFDRAW(1:8)//' DUMP A'
ELSE
FILNAM = CFDRAW
END IF
call iaea_new_source(source_write,FILNAM,access_write,result)
if( result.lt.0 ) then
write(LUNERR,*) 'Error create new source'
call flush(LUNERR)
call exit(1)
end if
iextrafloat = 0
iextralong = 0
call iaea_set_extra_numbers(source_write,iextrafloat,iextralong)
REGFROMNAMEs = REGFROMNAME
REGTONAMEs = REGTONAME
CALL GEON2R(REGFROMNAMEs, REGFROMNUM , IERR1)
CALL GEON2R(REGTONAMEs, REGTONUM, IERR2)
END IF
IF (REGFROMNUM.eq.MREG .AND. REGTONUM.eq.NEWREG) THEN
IF (JTRACK.ge.1 .AND. JTRACK.le.8
& .AND. IAEAParticle(JTRACK).ne.-1) THEN
72
typ = IAEAParticle(JTRACK)
IF (typ .ne. -1) then
E = (ETRACK - AM(JTRACK))*1000
wt = WTRACK
x = xsco
y = ysco
z = zsco
u = cxtrck
v = cytrck
w = cztrck
call iaea_write_particle(source_write,n_stat,typ,E,wt,x,y,z,
&
u,v,w,extra_floats,extra_ints)
totalorghist = 100
call iaea_set_total_original_particles(source_write,
& totalorghist)
call iaea_update_header(source_write, IAEA_I32 *result)
end if
END IF
END IF
RETURN
*
*======================================================================*
*
*
*
Event End DRAWing:
*
*
*
*======================================================================*
*
*
ENTRY EEDRAW ( ICODE )
RETURN
*
*======================================================================*
*
*
*
ENergy deposition DRAWing:
*
*
*
*
Icode = 1x: call from Kaskad
*
*
10: elastic interaction recoil
*
11: inelastic interaction recoil
*
12: stopping particle
*
13: pseudo-neutron deposition
*
14: escape
*
15: time kill
*
*
*
*
*
*
*
Icode = 2x: call from Emfsco
*
*
20: local energy deposition (i.e. photoelectric)
*
21: below threshold, iarg=1
*
22: below threshold, iarg=2
*
23: escape
*
24: time kill
*
*
*
*
Icode = 3x: call from Kasneu
*
*
30: target recoil
*
31: below threshold
*
32: escape
*
33: time kill
*
*
*
*
*
*
Icode = 4x: call from Kashea
40: escape
*
*
*
*
73
*
41: time kill
*
42: delta ray stack overflow
*
*
*
Icode = 5x: call from Kasoph
*
*
50: optical photon absorption
*
51: escape
*
*
52: time kill
*
*
*
*
*======================================================================*
*
*
ENTRY ENDRAW ( ICODE, MREG, RULL, XSCO, YSCO, ZSCO )
RETURN
*
*======================================================================*
*
*
*
SOurce particle DRAWing:
*
*
*
*======================================================================*
*
ENTRY SODRAW
* +-------------------------------------------------------------------*
RETURN
*
*======================================================================*
*
*
*
USer dependent DRAWing:
*
*
*
*
Icode = 10x: call from Kaskad
*
*
100: elastic interaction secondaries
*
101: inelastic interaction secondaries
*
102: particle decay secondaries
*
103: delta ray generation secondaries
*
104: pair production secondaries
*
105: bremsstrahlung secondaries
*
110: decay products
*
Icode = 20x: call from Emfsco
*
*
*
*
*
*
*
*
*
208: bremsstrahlung secondaries
*
210: Moller secondaries
*
212: Bhabha secondaries
*
214: in-flight annihilation secondaries
*
215: annihilation at rest secondaries
*
*
217: pair production
*
*
219: Compton scattering
*
221: photoelectric
*
*
*
*
*
*
*
*
*
secondaries
secondaries
secondaries
225: Rayleigh scattering
*
*
secondaries
*
Icode = 30x: call from Kasneu
*
300: interaction secondaries
*
Icode = 40x: call from Kashea
*
400: delta ray generation secondaries
*
* For all interactions secondaries are put on GENSTK common (kp=1,np) *
* but for KASHEA delta ray generation where only the secondary elec- *
* tron is present and stacked on FLKSTK common for kp=npflka
*
*
*
*======================================================================*
*
ENTRY USDRAW ( ICODE, MREG, XSCO, YSCO, ZSCO )
RETURN
*=== End of subrutine Mgdraw ==========================================*
74
END
A.3: User Routine usrmed.f for Solving the particles
double counting problem
*$ CREATE USRMED.FOR
*COPY USRMED
*
*
*=== usrmed ===========================================================*
*
*
#define REGFROMNAME "TARGET"
#define REGTONAME "VOID"
SUBROUTINE USRMED ( IJ, EKSCO, PLA, WEE, MREG, NEWREG, XX, YY, ZZ,
&
TXX, TYY, TZZ )
INCLUDE '(DBLPRC)'
INCLUDE '(DIMPAR)'
INCLUDE '(IOUNIT)'
*
*----------------------------------------------------------------------*
*
*
* Copyright (C) 1991-2005 by Alfredo Ferrari & Paola Sala *
* All Rights Reserved.
*
*
*
*
*
* USeR MEDium dependent directives:
*
*
*
* Created on 10 may 1996 by Alfredo Ferrari & Paola Sala *
*
Infn - Milan
*
*
*
* Last change on 29-may-96 by Alfredo Ferrari
*
*
*
* Input variables:
*
*
ij = particle id
*
*
Eksco = particle kinetic energy (GeV)
*
*
Pla = particle momentum (GeV/c)
*
*
Wee = particle weight
*
*
Mreg = (original) region number
*
*
Newreg = (final) region number
*
*
Xx,Yy,Zz = particle position
*
* Txx,Tyy,Tzz = particle direction
*
*
*
* The user is supposed to change only WEE if MREG = NEWREG and
* WEE, NEWREG, TXX, TYY, TZZ if MREG .NE. NEWREG
*
*
*----------------------------------------------------------------------*
CHARACTER*8 REGFROMNAMEs, REGTONAMEs
INTEGER IERR1, IERR2
LOGICAL LFIRST
SAVE LFIRST
DATA LFIRST /.TRUE./
75
*
*
INTEGER REGFROMNUM, REGTONUM
SAVE REGFROMNUM, REGTONUM
IF (LFIRST) THEN
REGFROMNAMEs = REGFROMNAME
REGTONAMEs = REGTONAME
CALL GEON2R(REGFROMNAMEs, REGFROMNUM , IERR1)
CALL GEON2R(REGTONAMEs, REGTONUM, IERR2)
LFIRST = .FALSE.
END IF
IF (REGFROMNUM.eq.Mreg .AND. REGTONUM.eq.Newreg) THEN
WEE = ZERZER
END IF
RETURN
*=== End of subroutine Usrmed =========================================*
END
A.4: FLUKA input file for collecting Patient-Scattered
Radiation
TITLE
#define FIELDSIZECM 5
* Set the defaults for precision simulations
DEFAULTS
PRECISIO
* Define the beam characteristics
BEAM
-1.0
PHOTON
* Define the beam position
BEAMPOS
SOURCE
!@what.3=-atan2(FIELDSIZECM/2,100)*180/pi
ROT-DEFI
101.
0.0-1.1457628
UJ1ROT
!@what.3=atan2(FIELDSIZECM/2,100)*180/pi
ROT-DEFI
102.
0.01.14576284
UJ2ROT
!@what.3=atan2(FIELDSIZECM/2,100)*180/pi
ROT-DEFI
203.
0.01.14576284
LJ1ROT
!@what.3=-atan2(FIELDSIZECM/2,100)*180/pi
ROT-DEFI
204.
0.0-1.1457628
LJ2ROT
GEOBEGIN
COMBNAME
0 0
* Black body
SPH blkbody 0.0 0.0 0.0 100000.0
* Void sphere
SPH void
0.0 0.0 0.0 10000.0
SPH target 0.0 0.0 100. 20.
$start_transform UJ1ROT
!@what.1=-15
!@what.2=15
!@what.3=-15
!@what.4=0
!@what.5=28
!@what.6=28+7.8
76
RPP UJ1
-15. 15. -15. 0.0 28. 35.8
$end_transform
$start_transform UJ2ROT
!@what.1=-15
!@what.2=15
!@what.3=0
!@what.4=15
!@what.5=28
!@what.6=28+7.8
RPP UJ2
-15. 15. 0.0 15. 28. 35.8
$end_transform
$start_transform LJ1ROT
!@what.1=-15
!@what.2=0
!@what.3=-15
!@what.4=+15
!@what.5=36.7
!@what.6=36.7+7.8
RPP LJ1
-15. 0.0 -15. 15. 36.7 44.5
$end_transform
$start_transform LJ2ROT
!@what.1=0
!@what.2=15
!@what.3=-15
!@what.4=+15
!@what.5=36.7
!@what.6=36.7+7.8
RPP LJ2
0.0 15. -15. 15. 36.7 44.5
$end_transform
!@what.5=57.4-0.01
RPP GLASS
-25. 25. -25. 25. 57.39 57.4
END
* Black hole
BLKBODY
5 +blkbody -void
* Void around
VOID
5 +void - target -UJ1 -UJ2 -LJ1 -LJ2 -GLASS
* Target
TARGET
5 target
JAWS
5 UJ1
| UJ2
| LJ1
| LJ2
glassR
5 GLASS
END
GEOEND
*MAT-PROP
1.
AIR
AIR
USERDIRE
*MAT-PROP
1.
TISSUEIC TISSUEIC
USERDIRE
MATERIAL
15.
1.82
PHOSPHO
MATERIAL
16.
2.07
SULFUR
MATERIAL
17.
0.003214
CHLORINE
MATERIAL
19.
0.862
POTASSIU
MATERIAL
30.
7.133
ZINC
* Tissue soft (ICRP)
*
MATERIAL
1.0
TISSUEIC
COMPOUND -0.104472 HYDROGEN -0.23219 CARBON -0.02488 NITROGENTISSUEIC
COMPOUND -0.630238 OXYGEN -0.00113 SODIUM -0.00013 MAGNESIUTISSUEIC
COMPOUND -0.00133 PHOSPHO -0.00199 SULFUR -0.00134 CHLORINETISSUEIC
77
COMPOUND -0.00199 POTASSIU -0.00023 CALCIUM -5E-05 IRONTISSUEIC
COMPOUND
-3E-05 ZINC
TISSUEIC
* Mylar, Melinex
* Chemical Formula : H-C = C-H
H H
*
/
\
| |
*
---- O - C - C
C - C - O - C - C ------*
|| \\ // ||
| |
* C H0
O H-C - C-H O
H H
* 10 8 4
MATERIAL
1.397
Mylar
COMPOUND
8.0 HYDROGEN 10.0 CARBON
4.0 OXYGENMylar
* ..+....1....+....2....+....3....+....4....+....5....+....6....+....7..
ASSIGNMA BLCKHOLE BLKBODY
ASSIGNMA
AIR
VOID
ASSIGNMA TISSUEIC TARGET
ASSIGNMA
Mylar glassR
ASSIGNMA TUNGSTEN
JAWS
USERDUMP
100.
22.
2.
0.0
dump
* Set the random number seed
RANDOMIZ
1.01258973038
* Set the number of primary histories to be simulated in the run
START
1000000.
STOP
78
A.5: FLUKA input file for collecting Transmission data
of Patient-Scattered Radiation in Concrete
TITLE
#define Thicknes 200
#define BA0 1
#define BA1 44959.22533
#define BB0 2.93367
#define BB1 340866156
#define BC0 2.993
#define BC1 334083615
#define BD0 49.697
#define BD1 20121537
#define BE0 503.9439
#define BE1 1984327.983
* Set the defaults for precision simulations
DEFAULTS
PRECISIO
* Define the beam characteristics
BEAM
-1.0
PHOTON
* Define the beam position
BEAMPOS
SOURCE
GEOBEGIN
COMBNAME
0 0
* Black body
SPH blkbody 0.0 0.0 0.0 100000.0
* Void sphere
SPH void
0.0 0.0 0.0 10000.0
SPH target
0.0 0.0 100. 20.
!@what.4=300+Thicknes/20*0
SPH wall0
0.0 0.0 100. 300.
!@what.4=300+Thicknes/20*1
SPH wall1
0.0 0.0 100. 310.
!@what.4=300+Thicknes/20*2
SPH wall2
0.0 0.0 100. 320.
!@what.4=300+Thicknes/20*3
SPH wall3
0.0 0.0 100. 330.
!@what.4=300+Thicknes/20*4
SPH wall4
0.0 0.0 100. 340.
!@what.4=300+Thicknes/20*5
SPH wall5
0.0 0.0 100. 350.
!@what.4=300+Thicknes/20*6
SPH wall6
0.0 0.0 100. 360.
!@what.4=300+Thicknes/20*7
SPH wall7
0.0 0.0 100. 370.
!@what.4=300+Thicknes/20*8
SPH wall8
0.0 0.0 100. 380.
!@what.4=300+Thicknes/20*9
SPH wall9
0.0 0.0 100. 390.
!@what.4=300+Thicknes/20*10
SPH wall10
0.0 0.0 100. 400.
79
!@what.4=300+Thicknes/20*11
SPH wall11
0.0 0.0 100. 410.
!@what.4=300+Thicknes/20*12
SPH wall12
0.0 0.0 100. 420.
!@what.4=300+Thicknes/20*13
SPH wall13
0.0 0.0 100. 430.
!@what.4=300+Thicknes/20*14
SPH wall14
0.0 0.0 100. 440.
!@what.4=300+Thicknes/20*15
SPH wall15
0.0 0.0 100. 450.
!@what.4=300+Thicknes/20*16
SPH wall16
0.0 0.0 100. 460.
!@what.4=300+Thicknes/20*17
SPH wall17
0.0 0.0 100. 470.
!@what.4=300+Thicknes/20*18
SPH wall18
0.0 0.0 100. 480.
!@what.4=300+Thicknes/20*19
SPH wall19
0.0 0.0 100. 490.
!@what.4=300+Thicknes/20*20
SPH wall20
0.0 0.0 100. 500.
!@what.8=5000*tan(3.141592654*10/180)
TRC ang10
0.0 0.0 100. 0.0 0.0 5000. 0.0 881.634903659814
!@what.8=5000*tan(3.141592654*40/180)
TRC ang40
0.0 0.0 100. 0.0 0.0 5000. 0.0 4195.498156663099
!@what.8=5000*tan(3.141592654*50/180)
TRC ang50
0.0 0.0 100. 0.0 0.0 5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*85/180)
TRC ang85
0.0 0.0 100. 0.0 0.0 5000. 0.0 57150.26164131165
!@what.8=5000*tan(3.141592654*85/180)
TRC ang95
0.0 0.0 100. 0.0 0.0 -5000. 0.0 57150.26164131165
!@what.8=5000*tan(3.141592654*50/180)
TRC ang130
0.0 0.0 100. 0.0 0.0 -5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*40/180)
TRC ang140
0.0 0.0 100. 0.0 0.0 -5000. 0.0 4195.498156663099
!@what.8=5000*tan(3.141592654*10/180)
TRC ang170
0.0 0.0 100. 0.0 0.0 -5000. 0.0 881.634903659814
!@what.4=300-10
SPH walln1
0.0 0.0 100. 290.
!@what.4=300-20
SPH walln2
0.0 0.0 100. 280.
!@what.4=300-30
SPH walln3
0.0 0.0 100. 270.
!@what.4=300-40
SPH walln4
0.0 0.0 100. 260.
!@what.4=300+Thicknes/20*1
SPH wall21
0.0 0.0 100. 310.
!@what.4=300+Thicknes/20*0
SPH wall22
0.0 0.0 100. 300.
!@what.8=5000*tan(3.141592654*10/180)
TRC ang11
0.0 0.0 100. 0.0 0.0 5000. 0.0 881.634903659814
!@what.4=300+Thicknes/20*0
SPH wall23
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln5
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*10/180)
TRC ang12
0.0 0.0 100. 0.0 0.0 5000. 0.0 881.634903659814
!@what.4=300+Thicknes/20*0
SPH wall24
0.0 0.0 100. 300.
80
!@what.4=300-10
SPH walln6
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*10/180)
TRC ang13
0.0 0.0 100. 0.0 0.0 5000. 0.0 881.634903659814
!@what.4=300+Thicknes/20*0
SPH wall25
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln7
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*10/180)
TRC ang14
0.0 0.0 100. 0.0 0.0 5000. 0.0 881.634903659814
!@what.4=300+Thicknes/20*1
SPH wall26
0.0 0.0 100. 310.
!@what.4=300+Thicknes/20*0
SPH wall27
0.0 0.0 100. 300.
!@what.8=5000*tan(3.141592654*50/180)
TRC ang51
0.0 0.0 100. 0.0 0.0 5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*40/180)
TRC ang41
0.0 0.0 100. 0.0 0.0 5000. 0.0 4195.498156663099
!@what.4=300+Thicknes/20*0
SPH wall28
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln8
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*50/180)
TRC ang52
0.0 0.0 100. 0.0 0.0 5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*40/180)
TRC ang42
0.0 0.0 100. 0.0 0.0 5000. 0.0 4195.498156663099
!@what.4=300+Thicknes/20*0
SPH wall29
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln9
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*50/180)
TRC ang53
0.0 0.0 100. 0.0 0.0 5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*40/180)
TRC ang43
0.0 0.0 100. 0.0 0.0 5000. 0.0 4195.498156663099
!@what.4=300+Thicknes/20*0
SPH wall30
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln10
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*50/180)
TRC ang54
0.0 0.0 100. 0.0 0.0 5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*40/180)
TRC ang44
0.0 0.0 100. 0.0 0.0 5000. 0.0 4195.498156663099
!@what.4=300+Thicknes/20*1
SPH wall31
0.0 0.0 100. 310.
!@what.4=300+Thicknes/20*0
SPH wall32
0.0 0.0 100. 300.
!@what.8=5000*tan(3.141592654*85/180)
TRC ang86
0.0 0.0 100. 0.0 0.0 5000. 0.0 57150.26164131165
!@what.8=5000*tan(3.141592654*85/180)
TRC ang96
0.0 0.0 100. 0.0 0.0 -5000. 0.0 57150.26164131165
!@what.4=300+Thicknes/20*0
SPH wall33
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln11
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*85/180)
TRC ang87
0.0 0.0 100. 0.0 0.0 5000. 0.0 57150.26164131165
!@what.8=5000*tan(3.141592654*85/180)
TRC ang97
0.0 0.0 100. 0.0 0.0 -5000. 0.0 57150.26164131165
81
!@what.4=300+Thicknes/20*0
SPH wall34
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln12
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*85/180)
TRC ang88
0.0 0.0 100. 0.0 0.0 5000. 0.0 57150.26164131165
!@what.8=5000*tan(3.141592654*85/180)
TRC ang98
0.0 0.0 100. 0.0 0.0 -5000. 0.0 57150.26164131165
!@what.4=300+Thicknes/20*0
SPH wall35
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln13
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*85/180)
TRC ang89
0.0 0.0 100. 0.0 0.0 5000. 0.0 57150.26164131165
!@what.8=5000*tan(3.141592654*85/180)
TRC ang99
0.0 0.0 100. 0.0 0.0 -5000. 0.0 57150.26164131165
!@what.4=300+Thicknes/20*1
SPH wall36
0.0 0.0 100. 310.
!@what.4=300+Thicknes/20*0
SPH wall37
0.0 0.0 100. 300.
!@what.8=5000*tan(3.141592654*50/180)
TRC ang131
0.0 0.0 100. 0.0 0.0 -5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*40/180)
TRC ang141
0.0 0.0 100. 0.0 0.0 -5000. 0.0 4195.498156663099
!@what.4=300+Thicknes/20*0
SPH wall38
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln14
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*50/180)
TRC ang132
0.0 0.0 100. 0.0 0.0 -5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*40/180)
TRC ang142
0.0 0.0 100. 0.0 0.0 -5000. 0.0 4195.498156663099
!@what.4=300+Thicknes/20*0
SPH wall39
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln15
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*50/180)
TRC ang133
0.0 0.0 100. 0.0 0.0 -5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*40/180)
TRC ang143
0.0 0.0 100. 0.0 0.0 -5000. 0.0 4195.498156663099
!@what.4=300+Thicknes/20*0
SPH wall40
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln16
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*50/180)
TRC ang134
0.0 0.0 100. 0.0 0.0 -5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*40/180)
TRC ang144
0.0 0.0 100. 0.0 0.0 -5000. 0.0 4195.498156663099
!@what.4=300+Thicknes/20*1
SPH wall41
0.0 0.0 100. 310.
!@what.4=300+Thicknes/20*0
SPH wall42
0.0 0.0 100. 300.
!@what.8=5000*tan(3.141592654*10/180)
TRC ang171
0.0 0.0 100. 0.0 0.0 -5000. 0.0 881.634903659814
!@what.4=300+Thicknes/20*0
SPH wall43
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln17
0.0 0.0 100. 290.
82
!@what.8=5000*tan(3.141592654*10/180)
TRC ang172
0.0 0.0 100. 0.0 0.0 -5000. 0.0 881.634903659814
!@what.4=300+Thicknes/20*0
SPH wall44
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln18
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*10/180)
TRC ang173
0.0 0.0 100. 0.0 0.0 -5000. 0.0 881.634903659814
!@what.4=300+Thicknes/20*0
SPH wall45
0.0 0.0 100. 300.
!@what.4=300-10
SPH walln19
0.0 0.0 100. 290.
!@what.8=5000*tan(3.141592654*10/180)
TRC ang174
0.0 0.0 100. 0.0 0.0 -5000. 0.0 881.634903659814
* Void sphere
SPH void1
0.0 0.0 0.0 10000.0
SPH target1 0.0 0.0 100. 20.
!@what.4=300+Thicknes/20*20
SPH wall46
0.0 0.0 100. 500.
!@what.4=300-40
SPH walln20
0.0 0.0 100. 260.
* Void sphere
SPH void2
0.0 0.0 0.0 10000.0
SPH target2 0.0 0.0 100. 20.
!@what.4=300-40
SPH walln21
0.0 0.0 100. 260.
!@what.4=300+Thicknes/20*0
SPH wall47
0.0 0.0 100. 300.
!@what.8=5000*tan(3.141592654*10/180)
TRC ang15
0.0 0.0 100. 0.0 0.0 5000. 0.0 881.634903659814
!@what.8=5000*tan(3.141592654*40/180)
TRC ang45
0.0 0.0 100. 0.0 0.0 5000. 0.0 4195.498156663099
!@what.8=5000*tan(3.141592654*50/180)
TRC ang55
0.0 0.0 100. 0.0 0.0 5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*85/180)
TRC ang90
0.0 0.0 100. 0.0 0.0 5000. 0.0 57150.26164131165
!@what.8=5000*tan(3.141592654*85/180)
TRC ang100
0.0 0.0 100. 0.0 0.0 -5000. 0.0 57150.26164131165
!@what.8=5000*tan(3.141592654*50/180)
TRC ang135
0.0 0.0 100. 0.0 0.0 -5000. 0.0 5958.767964349957
!@what.8=5000*tan(3.141592654*40/180)
TRC ang145
0.0 0.0 100. 0.0 0.0 -5000. 0.0 4195.498156663099
!@what.8=5000*tan(3.141592654*10/180)
TRC ang175
0.0 0.0 100. 0.0 0.0 -5000. 0.0 881.634903659814
END
* Black hole
BLKBODY
5 +blkbody -void
* Void around
VOID
5 +void -target +( +walln4)
| +(-walln4 +wall0) -ang10 +ang40 +void -target
| +(-walln4 +wall0) -ang50 +ang85 +void -target
| +(-walln4 +wall0) +ang95 -ang130 +void -target
| +(-walln4 +wall0) +ang140 -ang170 +void -target
* Target
TARGET
5 target
A1
5 +wall1 -wall0 +ang10
A2
5 +wall2 -wall1 +ang10
A3
5 +wall3 -wall2 +ang10
83
A4
5 +wall4-wall3 +ang10
A5
5 +wall5-wall4 +ang10
A6
5 +wall6 -wall5 +ang10
A7
5 +wall7 -wall6 +ang10
A8
5 +wall8 -wall7 +ang10
A9
5 +wall9 -wall8 +ang10
A10
5 +wall10 -wall9 +ang10
A11
5 +wall11 -wall10 +ang10
A12
5 +wall12 -wall11 +ang10
A13
5 +wall13 -wall12 +ang10
A14
5 +wall14 -wall13 +ang10
A15
5 +wall15 -wall14 +ang10
A16
5 +wall16 -wall15 +ang10
A17
5 +wall17 -wall16 +ang10
A18
5 +wall18 -wall17 +ang10
A19
5 +wall19 -wall18 +ang10
A20
5 +wall20 -wall19 +ang10
B1
5 +wall1 -wall0 +ang50 -ang40
B2
5 +wall2 -wall1 +ang50 -ang40
B3
5 +wall3 -wall2 +ang50 -ang40
B4
5 +wall4-wall3 +ang50 -ang40
B5
5 +wall5-wall4 +ang50 -ang40
B6
5 +wall6 -wall5 +ang50 -ang40
B7
5 +wall7 -wall6 +ang50 -ang40
B8
5 +wall8 -wall7 +ang50 -ang40
B9
5 +wall9 -wall8 +ang50 -ang40
B10
5 +wall10 -wall9 +ang50 -ang40
B11
5 +wall11 -wall10 +ang50 -ang40
B12
5 +wall12 -wall11 +ang50 -ang40
B13
5 +wall13 -wall12 +ang50 -ang40
B14
5 +wall14 -wall13 +ang50 -ang40
B15
5 +wall15 -wall14 +ang50 -ang40
B16
5 +wall16 -wall15 +ang50 -ang40
B17
5 +wall17 -wall16 +ang50 -ang40
B18
5 +wall18 -wall17 +ang50 -ang40
B19
5 +wall19 -wall18 +ang50 -ang40
B20
5 +wall20 -wall19 +ang50 -ang40
C1
5 +wall1 -wall0 -ang85 -ang95
C2
5 +wall2 -wall1 -ang85 -ang95
C3
5 +wall3 -wall2 -ang85 -ang95
C4
5 +wall4-wall3 -ang85 -ang95
C5
5 +wall5-wall4 -ang85 -ang95
C6
5 +wall6 -wall5 -ang85 -ang95
C7
5 +wall7 -wall6 -ang85 -ang95
C8
5 +wall8 -wall7 -ang85 -ang95
C9
5 +wall9 -wall8 -ang85 -ang95
C10
5 +wall10 -wall9 -ang85 -ang95
C11
5 +wall11 -wall10 -ang85 -ang95
C12
5 +wall12 -wall11 -ang85 -ang95
C13
5 +wall13 -wall12 -ang85 -ang95
C14
5 +wall14 -wall13 -ang85 -ang95
C15
5 +wall15 -wall14 -ang85 -ang95
C16
5 +wall16 -wall15 -ang85 -ang95
C17
5 +wall17 -wall16 -ang85 -ang95
C18
5 +wall18 -wall17 -ang85 -ang95
C19
5 +wall19 -wall18 -ang85 -ang95
C20
5 +wall20 -wall19 -ang85 -ang95
D1
5 +wall1 -wall0 +ang130 -ang140
84
D2
5 +wall2 -wall1 +ang130 -ang140
D3
5 +wall3 -wall2 +ang130 -ang140
D4
5 +wall4-wall3 +ang130 -ang140
D5
5 +wall5-wall4 +ang130 -ang140
D6
5 +wall6 -wall5 +ang130 -ang140
D7
5 +wall7 -wall6 +ang130 -ang140
D8
5 +wall8 -wall7 +ang130 -ang140
D9
5 +wall9 -wall8 +ang130 -ang140
D10
5 +wall10 -wall9 +ang130 -ang140
D11
5 +wall11 -wall10 +ang130 -ang140
D12
5 +wall12 -wall11+ang130 -ang140
D13
5 +wall13 -wall12 +ang130 -ang140
D14
5 +wall14 -wall13 +ang130 -ang140
D15
5 +wall15 -wall14 +ang130 -ang140
D16
5 +wall16 -wall15 +ang130 -ang140
D17
5 +wall17 -wall16 +ang130 -ang140
D18
5 +wall18 -wall17+ang130 -ang140
D19
5 +wall19 -wall18 +ang130 -ang140
D20
5 +wall20 -wall19 +ang130 -ang140
E1
5 +wall1 -wall0 +ang170
E2
5 +wall2 -wall1 +ang170
E3
5 +wall3 -wall2 +ang170
E4
5 +wall4-wall3 +ang170
E5
5 +wall5-wall4 +ang170
E6
5 +wall6 -wall5 +ang170
E7
5 +wall7 -wall6 +ang170
E8
5 +wall8 -wall7 +ang170
E9
5 +wall9 -wall8 +ang170
E10
5 +wall10 -wall9 +ang170
E11
5 +wall11 -wall10 +ang170
E12
5 +wall12 -wall11+ang170
E13
5 +wall13 -wall12 +ang170
E14
5 +wall14 -wall13 +ang170
E15
5 +wall15 -wall14 +ang170
E16
5 +wall16 -wall15 +ang170
E17
5 +wall17 -wall16 +ang170
E18
5 +wall18 -wall17+ang170
E19
5 +wall19 -wall18 +ang170
E20
5 +wall20 -wall19 +ang170
BHbet
5 +wall20 -wall0 +(+ang140 -ang170 | -ang130 +ang95 | -ang50 +ang85|+ang40-ang10)
A0
5 +wall0 -walln1 +ang10
An1
5 +walln1 -walln2 +ang10
An2
5 +walln2 -walln3 +ang10
An3
5 +walln3 -walln4 +ang10
B0
5 +wall0 -walln1 +ang50 -ang40
Bn1
5 +walln1 -walln2 +ang50 -ang40
Bn2
5 +walln2 -walln3 +ang50 -ang40
Bn3
5 +walln3 -walln4 +ang50 -ang40
C0
5 +wall0 -walln1 -ang85 -ang95
Cn1
5 +walln1 -walln2 -ang85 -ang95
Cn2
5 +walln2 -walln3 -ang85 -ang95
Cn3
5 +walln3 -walln4 -ang85 -ang95
D0
5 +wall0 -walln1 +ang130 -ang140
Dn1
5 +walln1 -walln2 +ang130 -ang140
Dn2
5 +walln2 -walln3 +ang130 -ang140
Dn3
5 +walln3 -walln4 +ang130 -ang140
* Void around
VOID1
5 +void -target -wall20
85
E0
5 +wall0 -walln1 +ang170
En1
5 +walln1 -walln2 +ang170
En2
5 +walln2 -walln3 +ang170
En3
5 +walln3 -walln4 +ang170
END
GEOEND
* Avoid Back and forh
*
*MAT-PROP
1.
MATERIAL
15.
MATERIAL
MATERIAL
AIR
AIR
USERDIRE
1.82
PHOSPHO
16.
2.07
SULFUR
17.
0.003214
MATERIAL
19.
0.862
POTASSIU
MATERIAL
30.
7.133
ZINC
CHLORINE
* Tissue soft (ICRP)
*
MATERIAL
1.0
TISSUEIC
COMPOUND -0.104472 HYDROGEN -0.23219
CARBON -0.02488 NITROGENTISSUEIC
COMPOUND -0.630238 OXYGEN -0.00113 SODIUM -0.00013 MAGNESIUTISSUEIC
COMPOUND
-0.00133 PHOSPHO -0.00199 SULFUR -0.00134 CHLORINETISSUEIC
COMPOUND
-0.00199 POTASSIU -0.00023 CALCIUM
COMPOUND
-3E-05
ZINC
-5E-05
IRONTISSUEIC
TISSUEIC
* Mylar, Melinex
* Chemical Formula : H-C = C-H
*
*
/
\
---- O - C - C
*
|| \\
* C H0
H H
| |
C - C - O - C - C -------
//
||
| |
O H-C - C-H O
H H
* 10 8 4
MATERIAL
COMPOUND
1.397
8.0 HYDROGEN
Mylar
10.0 CARBON
4.0 OXYGENMylar
* HKconcrete
*
* The composition of the concrete is confidential *
* ..+....1....+....2....+....3....+....4....+....5....+....6....+....7..
ASSIGNMA
BLCKHOLE BLKBODY
ASSIGNMA
AIR
ASSIGNMA
AIR
VOID
A0
ASSIGNMA
AIR
An1
ASSIGNMA
AIR
An2
ASSIGNMA
AIR
B0
ASSIGNMA
AIR
Bn1
ASSIGNMA
AIR
Bn2
ASSIGNMA
AIR
Bn3
ASSIGNMA
AIR
VOID1
ASSIGNMA
AIR
C0
ASSIGNMA
AIR
Cn1
ASSIGNMA
AIR
Cn2
ASSIGNMA
AIR
Cn3
ASSIGNMA
AIR
D0
ASSIGNMA
AIR
Dn1
ASSIGNMA
AIR
Dn2
ASSIGNMA
AIR
Dn3
ASSIGNMA
AIR
An3
ASSIGNMA
AIR
E0
ASSIGNMA
AIR
En1
ASSIGNMA
AIR
En2
ASSIGNMA
AIR
En3
86
ASSIGNMA
TISSUEIC TARGET
ASSIGNMA
BLCKHOLE
ASSIGNMA
HKconc
BIASING
0.0
BHbet
A1
E20
0.0001 BLKBODY @LASTREG
1.PRINT
!@what.3=0.0001*pow(BA0,1.0/4)
BIASING
0.0
0.0001
An3
1.PRINT
An2
1.PRINT
An1
1.PRINT
A0
1.PRINT
!@what.3=0.0001*pow(BA0,2.0/4)
BIASING
0.0
0.0001
!@what.3=0.0001*pow(BA0,3.0/4)
BIASING
0.0
0.0001
!@what.3=0.0001*pow(BA0,4.0/4)
BIASING
0.0
0.0001
!@what.3=0.0001*BA0*pow(BA1,1.0/20)
BIASING
0.0
1.7086E-4
A1
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,2.0/20)
BIASING
0.0
2.91932E-4
A2
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,3.0/20)
BIASING
0.0
4.98796E-4
A3
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,4.0/20)
BIASING
0.0
8.52244E-4
A4
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,5.0/20)
BIASING
0.0
.001456145
A5
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,6.0/20)
BIASING
0.0
.002487973
A6
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,7.0/20)
BIASING
0.0
.004250956
A7
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,8.0/20)
BIASING
0.0
.007263192
A8
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,9.0/20)
BIASING
0.0
.012409905
A9
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,10.0/20)
BIASING
0.0
.021203591
A10
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,11.0/20)
BIASING
0.0
.0362285
A11
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,12.0/20)
BIASING
0.0
.061900092
A12
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,13.0/20)
BIASING
0.0
.105762628
A13
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,14.0/20)
BIASING
0.0
.18070625
A14
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,15.0/20)
BIASING
0.0
.308755082
A15
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,16.0/20)
BIASING
0.0
.527539588
A16
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,17.0/20)
BIASING
0.0
.901355258
A17
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,18.0/20)
BIASING
0.0
1.54005751
A18
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,19.0/20)
BIASING
0.0
2.63134552
A19
1.PRINT
!@what.3=0.0001*BA0*pow(BA1,20.0/20)
BIASING
0.0
4.49592253
A20
1.PRINT
Bn3
1.PRINT
Bn2
1.PRINT
Bn1
1.PRINT
!@what.3=0.0001*pow(BB0,1.0/4)
BIASING
0.0
1.30874E-4
!@what.3=0.0001*pow(BB0,2.0/4)
BIASING
0.0
1.7128E-4
!@what.3=0.0001*pow(BB0,3.0/4)
BIASING
0.0
2.2416E-4
87
!@what.3=0.0001*pow(BB0,4.0/4)
BIASING
0.0
2.93367E-4
B0
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,1.0/20)
BIASING
0.0
7.83503E-4
B1
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,2.0/20)
BIASING
0.0
.00209252
B2
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,3.0/20)
BIASING
0.0
.005588546
B3
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,4.0/20)
BIASING
0.0
.014925471
B4
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,5.0/20)
BIASING
0.0
.03986183
B5
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,6.0/20)
BIASING
0.0
.106459991
B6
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,7.0/20)
BIASING
0.0
.284325374
B7
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,8.0/20)
BIASING
0.0
.759354923
B8
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,9.0/20)
BIASING
0.0
2.02802828
B9
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,10.0/20)
BIASING
0.0
5.41630611
B10
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,11.0/20)
BIASING
0.0
14.4654649
B11
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,12.0/20)
BIASING
0.0
38.6332807
B12
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,13.0/20)
BIASING
0.0
103.178874
B13
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,14.0/20)
BIASING
0.0
275.562412
B14
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,15.0/20)
BIASING
0.0
735.951461
B15
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,16.0/20)
BIASING
0.0
1965.52407
B16
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,17.0/20)
BIASING
0.0
5249.37454
B17
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,18.0/20)
BIASING
0.0
14019.6365
B18
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,19.0/20)
BIASING
0.0
37442.5957
B19
1.PRINT
!@what.3=0.0001*BB0*pow(BB1,20.0/20)
BIASING
0.0
99998.8816
B20
1.PRINT
Cn3
1.PRINT
Cn2
1.PRINT
Cn1
1.PRINT
!@what.3=0.0001*pow(BC0,1.0/4)
BIASING
0.0
1.31531E-4
!@what.3=0.0001*pow(BC0,2.0/4)
BIASING
0.0
1.73003E-4
!@what.3=0.0001*pow(BC0,3.0/4)
BIASING
0.0
2.27552E-4
!@what.3=0.0001*pow(BC0,4.0/4)
BIASING
0.0
0.0002993
C0
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,1.0/20)
BIASING
0.0
7.98545E-4
C1
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,2.0/20)
BIASING
0.0
.002130552
C2
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,3.0/20)
BIASING
0.0
.005684405
C3
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,4.0/20)
BIASING
0.0
.015166234
C4
1.PRINT
88
!@what.3=0.0001*BC0*pow(BC1,5.0/20)
BIASING
0.0
.040464158
C5
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,6.0/20)
BIASING
0.0
.107960098
C6
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,7.0/20)
BIASING
0.0
.28804214
C7
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,8.0/20)
BIASING
0.0
.768508698
C8
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,9.0/20)
BIASING
0.0
2.05041394
C9
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,10.0/20)
BIASING
0.0
5.47059174
C10
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,11.0/20)
BIASING
0.0
14.5957718
C11
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,12.0/20)
BIASING
0.0
38.9421408
C12
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,13.0/20)
BIASING
0.0
103.89929
C13
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,14.0/20)
BIASING
0.0
277.207732
C14
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,15.0/20)
BIASING
0.0
739.602038
C15
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,16.0/20)
BIASING
0.0
1973.28974
C16
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,17.0/20)
BIASING
0.0
5264.82108
C17
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,18.0/20)
BIASING
0.0
14046.7669
C18
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,19.0/20)
BIASING
0.0
37477.3724
C19
1.PRINT
!@what.3=0.0001*BC0*pow(BC1,20.0/20)
BIASING
0.0
99991.226
C20
1.PRINT
Dn3
1.PRINT
Dn2
1.PRINT
Dn1
1.PRINT
!@what.3=0.0001*pow(BD0,1.0/4)
BIASING
0.0
2.65511E-4
!@what.3=0.0001*pow(BD0,2.0/4)
BIASING
0.0
7.04961E-4
!@what.3=0.0001*pow(BD0,3.0/4)
BIASING
0.0
.001871749
!@what.3=0.0001*pow(BD0,4.0/4)
BIASING
0.0
.0049697
D0
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,1.0/20)
BIASING
0.0
.011521612
D1
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,2.0/20)
BIASING
0.0
.026711378
D2
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,3.0/20)
BIASING
0.0
.061926901
D3
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,4.0/20)
BIASING
0.0
.143569571
D4
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,5.0/20)
BIASING
0.0
.332847624
D5
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,6.0/20)
BIASING
0.0
.771664495
D6
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,7.0/20)
BIASING
0.0
1.78900509
D7
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,8.0/20)
BIASING
0.0
4.14757868
D8
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,9.0/20)
BIASING
0.0
9.61562884
D9
1.PRINT
89
!@what.3=0.0001*BD0*pow(BD1,10.0/20)
BIASING
0.0
22.2926013
D10
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,11.0/20)
BIASING
0.0
51.6825349
D11
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,12.0/20)
BIASING
0.0
119.819324
D12
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,13.0/20)
BIASING
0.0
277.785723
D13
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,14.0/20)
BIASING
0.0
644.010546
D14
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,15.0/20)
BIASING
0.0
1493.05579
D15
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,16.0/20)
BIASING
0.0
3461.45822
D16
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,17.0/20)
BIASING
0.0
8024.94661
D17
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,18.0/20)
BIASING
0.0
18604.8087
D18
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,19.0/20)
BIASING
0.0
43132.8611
D19
1.PRINT
!@what.3=0.0001*BD0*pow(BD1,20.0/20)
BIASING
0.0
99998.0024
D20
1.PRINT
En3
1.PRINT
En2
1.PRINT
En1
1.PRINT
!@what.3=0.0001*pow(BE0,1.0/4)
BIASING
0.0
4.73801E-4
!@what.3=0.0001*pow(BE0,2.0/4)
BIASING
0.0
.002244869
!@what.3=0.0001*pow(BE0,3.0/4)
BIASING
0.0
.010636204
!@what.3=0.0001*pow(BE0,4.0/4)
BIASING
0.0
.05039439
E0
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,1.0/20)
BIASING
0.0
.104054979
E1
1.PRINT
E2
1.PRINT
E3
1.PRINT
E4
1.PRINT
E5
1.PRINT
E6
1.PRINT
E7
1.PRINT
E8
1.PRINT
E9
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,2.0/20)
BIASING
0.0
.214854047
!@what.3=0.0001*BE0*pow(BE1,3.0/20)
BIASING
0.0
.443633375
!@what.3=0.0001*BE0*pow(BE1,4.0/20)
BIASING
0.0
.916019848
!@what.3=0.0001*BE0*pow(BE1,5.0/20)
BIASING
0.0
1.89140946
!@what.3=0.0001*BE0*pow(BE1,6.0/20)
BIASING
0.0
3.90540636
!@what.3=0.0001*BE0*pow(BE1,7.0/20)
BIASING
0.0
8.06393285
!@what.3=0.0001*BE0*pow(BE1,8.0/20)
BIASING
0.0
16.6505113
!@what.3=0.0001*BE0*pow(BE1,9.0/20)
BIASING
0.0
34.3801881
!@what.3=0.0001*BE0*pow(BE1,10.0/20)
BIASING
0.0
70.9886506
E10
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,11.0/20)
BIASING
0.0
146.578271
E11
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,12.0/20)
BIASING
0.0
302.656682
E12
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,13.0/20)
BIASING
0.0
624.929375
E13
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,14.0/20)
BIASING
0.0
1290.36214
E14
1.PRINT
90
!@what.3=0.0001*BE0*pow(BE1,15.0/20)
BIASING
0.0
2664.3562
E15
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,16.0/20)
BIASING
0.0
5501.39664
E16
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,17.0/20)
BIASING
0.0
11359.3539
E17
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,18.0/20)
BIASING
0.0
23454.9388
E18
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,19.0/20)
BIASING
0.0
48430.0566
E19
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,20.0/20)
BIASING
0.0
99998.9983
E20
1.PRINT
!@what.3=0.0001*BE0*pow(BE1,20.0/20)
BIASING
0.0
99998.9983
VOID1
1.PRINT
* Produce Phase Space
USRBDX
101.
USRBDX
USRBDX
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
101.
PHOTON
-24.
A7
101.
PHOTON
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
A5
AF_4_5
A6
AF_5_6
A7
AF_6_7
A8
AF_7_8
72. &
-24.
A8
A9
AF_8_9
72. &
-24.
A9
A10
AF_9_10
72. &
-24.
A10
A11
AF_10_11
72. &
-24.
A11
A12
AF_11_12
72. &
-24.
A12
A13
AF_12_13
72. &
-24.
A13
A14
AF_13_14
72. &
-24.
A14
A15
AF_14_15
72. &
-24.
A15
A16
AF_15_16
72. &
-24.
A16
A17
AF_16_17
72. &
-24.
A17
A18
AF_17_18
72. &
-24.
A18
A19
AF_18_19
72. &
-24.
A19
500.
USRBDX
AF_3_4
72. &
500.
USRBDX
USRBDX
A6
500.
USRBDX
USRBDX
-24.
500.
USRBDX
USRBDX
PHOTON
A4
72. &
500.
USRBDX
USRBDX
A5
500.
USRBDX
USRBDX
-24.
500.
USRBDX
USRBDX
PHOTON
AF_2_3
72. &
500.
USRBDX
USRBDX
A4
500.
USRBDX
USRBDX
-24.
500.
USRBDX
USRBDX
PHOTON
A3
72. &
500.
USRBDX
USRBDX
A3
500.
USRBDX
USRBDX
-24.
500.
USRBDX
USRBDX
PHOTON
AF_1_2
72. &
500.
USRBDX
USRBDX
A2
500.
USRBDX
USRBDX
-24.
500.
USRBDX
USRBDX
PHOTON
A2
72. &
500.
USRBDX
USRBDX
A1
500.
USRBDX
USRBDX
-24.
500.
USRBDX
USRBDX
PHOTON
A20
AF_19_20
72. &
-24.
A20
VOID1
AF_20_21
72. &
-25.
A0
A1
AF_0_1
72. &
-25.
A1
A2
AF_1_2
91
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101.
USRBDX
USRBDX
101.
101.
101.
101.
101.
101.
101.
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
101.
PHOTON
-25.
A5
PHOTON
AF_3_4
A5
AF_4_5
A6
AF_5_6
72. &
-25.
A6
A7
AF_6_7
72. &
-25.
A7
A8
AF_7_8
72. &
-25.
A8
A9
AF_8_9
72. &
-25.
A9
A10
AF_9_10
72. &
-25.
A10
A11
AF_10_11
72. &
-25.
A11
A12
AF_11_12
72. &
-25.
A12
A13
AF_12_13
72. &
-25.
A13
A14
AF_13_14
72. &
-25.
A14
A15
AF_14_15
72. &
-25.
A15
A16
AF_15_16
72. &
-25.
A16
A17
AF_16_17
72. &
-25.
A17
A18
AF_17_18
72. &
-25.
A18
A19
AF_18_19
72. &
-25.
A19
A20
AF_19_20
72. &
-25.
A20
VOID1
AF_20_21
72. &
-34.
B1
B2
AF_1_2
72. &
-34.
B2
B3
AF_2_3
72. &
-34.
B3
B4
AF_3_4
72. &
-34.
B4
B5
AF_4_5
72. &
-34.
B5
B6
AF_5_6
72. &
-34.
B6
B7
AF_6_7
72. &
-34.
B7
B8
AF_7_8
72. &
-34.
B8
B9
AF_8_9
72. &
-34.
B9
500.
101.
A4
72. &
500.
USRBDX
USRBDX
A4
500.
USRBDX
USRBDX
-25.
500.
USRBDX
USRBDX
PHOTON
AF_2_3
72. &
500.
USRBDX
USRBDX
A3
500.
USRBDX
USRBDX
-25.
500.
USRBDX
USRBDX
PHOTON
A3
72. &
500.
USRBDX
USRBDX
A2
500.
USRBDX
USRBDX
PHOTON
72. &
-25.
B10
AF_9_10
72. &
-34.
B10
B11
AF_10_11
92
USRBDX
USRBDX
500.
101.
USRBDX
USRBDX
101.
101.
101.
101.
101.
101.
101.
B13
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
101.
PHOTON
-34.
B14
101.
PHOTON
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
AF_12_13
B14
AF_13_14
B15
AF_14_15
72. &
-34.
B15
B16
AF_15_16
72. &
-34.
B16
B17
AF_16_17
72. &
-34.
B17
B18
AF_17_18
72. &
-34.
B18
B19
AF_18_19
72. &
-34.
B19
500.
USRBDX
B13
72. &
500.
USRBDX
USRBDX
-34.
500.
USRBDX
USRBDX
PHOTON
AF_11_12
72. &
500.
USRBDX
USRBDX
B12
500.
USRBDX
USRBDX
-34.
500.
USRBDX
USRBDX
PHOTON
B12
72. &
500.
USRBDX
USRBDX
B11
500.
USRBDX
USRBDX
72. &
-34.
500.
USRBDX
USRBDX
PHOTON
B20
AF_19_20
72. &
-34.
B20
VOID1
AF_20_21
72. &
-35.
B0
B1
AF_0_1
72. &
-35.
B1
B2
AF_1_2
72. &
-35.
B2
B3
AF_2_3
72. &
-35.
B3
B4
AF_3_4
72. &
-35.
B4
B5
AF_4_5
72. &
-35.
B5
B6
AF_5_6
72. &
-35.
B6
B7
AF_6_7
72. &
-35.
B7
B8
AF_7_8
72. &
-35.
B8
B9
AF_8_9
72. &
-35.
B9
B10
AF_9_10
72. &
-35.
B10
B11
AF_10_11
72. &
-35.
B11
B12
AF_11_12
72. &
-35.
B12
B13
AF_12_13
72. &
-35.
B13
B14
AF_13_14
72. &
-35.
B14
B15
AF_14_15
72. &
-35.
B15
B16
AF_15_16
72. &
-35.
B16
B17
AF_16_17
72. &
-35.
B17
B18
AF_17_18
72. &
-35.
B18
B19
AF_18_19
93
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101.
USRBDX
USRBDX
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
C4
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
101.
PHOTON
-44.
C5
101.
PHOTON
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
AF_1_2
C3
AF_2_3
C4
AF_3_4
C5
AF_4_5
C6
AF_5_6
72. &
-44.
C6
C7
AF_6_7
72. &
-44.
C7
C8
AF_7_8
72. &
-44.
C8
C9
AF_8_9
72. &
-44.
C9
C10
AF_9_10
72. &
-44.
C10
C11
AF_10_11
72. &
-44.
C11
C12
AF_11_12
72. &
-44.
C12
C13
AF_12_13
72. &
-44.
C13
C14
AF_13_14
72. &
-44.
C14
C15
AF_14_15
72. &
-44.
C15
C16
AF_15_16
72. &
-44.
C16
C17
AF_16_17
72. &
-44.
C17
C18
AF_17_18
72. &
-44.
C18
C19
AF_18_19
72. &
-44.
C19
500.
USRBDX
C2
72. &
500.
USRBDX
USRBDX
-44.
500.
USRBDX
USRBDX
PHOTON
AF_0_1
72. &
500.
USRBDX
USRBDX
C3
500.
USRBDX
USRBDX
-44.
500.
USRBDX
USRBDX
PHOTON
C1
72. &
500.
USRBDX
USRBDX
C2
500.
USRBDX
USRBDX
-44.
500.
USRBDX
USRBDX
PHOTON
AF_20_21
72. &
500.
USRBDX
USRBDX
C1
500.
USRBDX
USRBDX
-44.
500.
USRBDX
USRBDX
PHOTON
VOID1
72. &
500.
USRBDX
USRBDX
C0
500.
USRBDX
USRBDX
-44.
500.
USRBDX
USRBDX
PHOTON
AF_19_20
72. &
500.
USRBDX
USRBDX
B20
500.
USRBDX
USRBDX
-35.
500.
USRBDX
USRBDX
PHOTON
B20
72. &
500.
USRBDX
USRBDX
B19
500.
USRBDX
USRBDX
PHOTON
72. &
-35.
C20
AF_19_20
72. &
-44.
C20
VOID1
AF_20_21
72. &
-45.
C0
C1
AF_0_1
72. &
-45.
C1
C2
AF_1_2
72. &
-45.
C2
C3
AF_2_3
72. &
-45.
C3
C4
AF_3_4
72. &
-45.
C4
C5
AF_4_5
72. &
-45.
C5
C6
AF_5_6
94
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101.
USRBDX
USRBDX
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
-45.
C10
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
101.
PHOTON
-45.
C11
PHOTON
AF_8_9
C10
AF_9_10
C11
AF_10_11
C12
AF_11_12
72. &
-45.
C12
C13
AF_12_13
72. &
-45.
C13
C14
AF_13_14
72. &
-45.
C14
C15
AF_14_15
72. &
-45.
C15
C16
AF_15_16
72. &
-45.
C16
C17
AF_16_17
72. &
-45.
C17
C18
AF_17_18
72. &
-45.
C18
C19
AF_18_19
72. &
-45.
C19
C20
AF_19_20
72. &
-45.
C20
VOID1
AF_20_21
72. &
-54.
D0
D1
AF_0_1
72. &
-54.
D1
D2
AF_1_2
72. &
-54.
D2
D3
AF_2_3
72. &
-54.
D3
D4
AF_3_4
72. &
-54.
D4
D5
AF_4_5
72. &
-54.
D5
D6
AF_5_6
72. &
-54.
D6
D7
AF_6_7
72. &
-54.
D7
D8
AF_7_8
72. &
-54.
D8
D9
AF_8_9
72. &
-54.
D9
D10
AF_9_10
72. &
-54.
D10
D11
AF_10_11
72. &
-54.
D11
D12
AF_11_12
72. &
-54.
D12
500.
101.
C9
72. &
500.
USRBDX
USRBDX
PHOTON
AF_7_8
72. &
500.
USRBDX
USRBDX
C9
500.
USRBDX
USRBDX
-45.
500.
USRBDX
USRBDX
PHOTON
C8
72. &
500.
USRBDX
USRBDX
C8
500.
USRBDX
USRBDX
-45.
500.
USRBDX
USRBDX
PHOTON
AF_6_7
72. &
500.
USRBDX
USRBDX
C7
500.
USRBDX
USRBDX
-45.
500.
USRBDX
USRBDX
PHOTON
C7
72. &
500.
USRBDX
USRBDX
C6
500.
USRBDX
USRBDX
PHOTON
72. &
-45.
D13
AF_12_13
72. &
-54.
D13
D14
AF_13_14
95
USRBDX
USRBDX
500.
101.
USRBDX
USRBDX
101.
101.
101.
101.
PHOTON
PHOTON
PHOTON
101.
PHOTON
101.
PHOTON
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
101.
PHOTON
AF_14_15
D16
AF_15_16
72. &
-54.
D16
D17
AF_16_17
72. &
-54.
D17
D18
AF_17_18
72. &
-54.
D18
D19
AF_18_19
72. &
-54.
D19
500.
USRBDX
USRBDX
D15
500.
USRBDX
USRBDX
-54.
500.
USRBDX
USRBDX
PHOTON
D15
72. &
500.
USRBDX
USRBDX
D14
500.
USRBDX
USRBDX
72. &
-54.
500.
USRBDX
USRBDX
PHOTON
D20
AF_19_20
72. &
-54.
D20
VOID1
AF_20_21
72. &
-55.
D0
D1
AF_0_1
72. &
-55.
D1
D2
AF_1_2
72. &
-55.
D2
D3
AF_2_3
72. &
-55.
D3
D4
AF_3_4
72. &
-55.
D4
D5
AF_4_5
72. &
-55.
D5
D6
AF_5_6
72. &
-55.
D6
D7
AF_6_7
72. &
-55.
D7
D8
AF_7_8
72. &
-55.
D8
D9
AF_8_9
72. &
-55.
D9
D10
AF_9_10
72. &
-55.
D10
D11
AF_10_11
72. &
-55.
D11
D12
AF_11_12
72. &
-55.
D12
D13
AF_12_13
72. &
-55.
D13
D14
AF_13_14
72. &
-55.
D14
D15
AF_14_15
72. &
-55.
D15
D16
AF_15_16
72. &
-55.
D16
D17
AF_16_17
72. &
-55.
D17
D18
AF_17_18
72. &
-55.
D18
D19
AF_18_19
72. &
-55.
D19
D20
AF_19_20
72. &
-55.
D20
VOID1
AF_20_21
72. &
-64.
E0
E1
AF_0_1
96
USRBDX
USRBDX
500.
101.
USRBDX
USRBDX
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
101.
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
PHOTON
101.
PHOTON
-64.
E7
101.
PHOTON
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
E5
AF_4_5
E6
AF_5_6
E7
AF_6_7
E8
AF_7_8
72. &
-64.
E8
E9
AF_8_9
72. &
-64.
E9
E10
AF_9_10
72. &
-64.
E10
E11
AF_10_11
72. &
-64.
E11
E12
AF_11_12
72. &
-64.
E12
E13
AF_12_13
72. &
-64.
E13
E14
AF_13_14
72. &
-64.
E14
E15
AF_14_15
72. &
-64.
E15
E16
AF_15_16
72. &
-64.
E16
E17
AF_16_17
72. &
-64.
E17
E18
AF_17_18
72. &
-64.
E18
E19
AF_18_19
72. &
-64.
E19
500.
USRBDX
AF_3_4
72. &
500.
USRBDX
USRBDX
E6
500.
USRBDX
USRBDX
-64.
500.
USRBDX
USRBDX
PHOTON
E4
72. &
500.
USRBDX
USRBDX
E5
500.
USRBDX
USRBDX
-64.
500.
USRBDX
USRBDX
PHOTON
AF_2_3
72. &
500.
USRBDX
USRBDX
E4
500.
USRBDX
USRBDX
-64.
500.
USRBDX
USRBDX
PHOTON
E3
72. &
500.
USRBDX
USRBDX
E3
500.
USRBDX
USRBDX
-64.
500.
USRBDX
USRBDX
PHOTON
AF_1_2
72. &
500.
USRBDX
USRBDX
E2
500.
USRBDX
USRBDX
-64.
500.
USRBDX
USRBDX
PHOTON
E2
72. &
500.
USRBDX
USRBDX
E1
500.
USRBDX
USRBDX
72. &
-64.
500.
USRBDX
USRBDX
PHOTON
E20
AF_19_20
72. &
-64.
E20
VOID1
AF_20_21
72. &
-65.
E0
E1
AF_0_1
72. &
-65.
E1
E2
AF_1_2
72. &
-65.
E2
E3
AF_2_3
72. &
-65.
E3
E4
AF_3_4
72. &
-65.
E4
E5
AF_4_5
72. &
-65.
E5
E6
AF_5_6
72. &
-65.
E6
E7
AF_6_7
72. &
-65.
E7
E8
AF_7_8
72. &
-65.
E8
E9
AF_8_9
97
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
USRBDX
101. DOSE-EQ
USRBDX
500.
72. &
-65.
E9
E10
AF_9_10
72. &
-65.
E10
E11
AF_10_11
72. &
-65.
E11
E12
AF_11_12
72. &
-65.
E12
E13
AF_12_13
72. &
-65.
E13
E14
AF_13_14
72. &
-65.
E14
E15
AF_14_15
72. &
-65.
E15
E16
AF_15_16
72. &
-65.
E16
E17
AF_16_17
72. &
-65.
E17
E18
AF_17_18
72. &
-65.
E18
E19
AF_18_19
72. &
-65.
E19
E20
AF_19_20
72. &
-65.
E20
VOID1
AF_20_21
72. &
* Set the random number seed
RANDOMIZ
1.01258973038
* Set the number of primary histories to be simulated in the run
START
STOP
100000000.
98