Study of Photoneutron Production for the 18 MV Photon Beam of the Siemens Medical linac by Monte Carlo Simulation.

BACKGROUND: Considering the importance of photoneutron production in linear accelerators, it is necessary to describe and measure the photoneutrons produced around modern linear accelerators.
OBJECTIVE: The aim of the present research is to study photoneutron production for the 18 MV photon beam of a Siemens Primus Plus medical linear accelerator.
MATERIAL AND METHODS: This study is an experimental study. The main components of the head of Siemens Primus Plus linac were simulated using MCNPX 2.7.0 code. The contribution of different components of the linac in photoneutron production, neutron source strength, neutron source strength and photon and electron spectra were calculated for the flattening filter and flattening filter free cases for the 18 MV photon beam, and was scored for three fields of 5 × 5 cm2, 10 × 10 cm2 and 20 × 20 cm2 in size.
RESULTS: The results show that the primary collimator has the largest contribution to production of neutrons. Moreover, the photon fluence for the flattening filter free case is 8.62, 6.51 and 4.62 times higher than the flattening filter case for the three fields, respectively. The electron fluences for the flattening filter free case are 4.62, 2.93 and 2.79 times higher than with flattening filter case for the three fields under study, respectively. In addition to these cases, by increasing the field size, the contribution of neutron production related to the jaws is reduced, so that when the field size increases from 5 × 5 cm2 to 20 × 20 cm2, a 17.93% decrease in photoneutron production was observed.
CONCLUSION: In all of the accelerators, the neutron strength also increases with increasing energy. The calculated neutron strength was equal to 0.83×1012 neutron Gy -1 at the isocenter. Copyright: © Journal of Biomedical Physics and Engineering.

Introduction

Radiotherapy is currently an essential component in the management of cancer patients, and radiotherapy using electron linear accelerators (linac) has an increasing role in treatment of cancerous tumors. On the other hand, medical linacs which operate above 10 MV for high energy photon therapy inevitably produce neutron contamination. Neutrons are produced through (γ, n) photonuclear reaction in the components of the head of linacs [ 1 - 3 ].

The energy threshold for a photonuclear reaction depends on the atomic number of material (Z), and by increasing the value of Z the energy threshold decreases [ 4 - 5 ]. Neutrons produced in the head of a linac have an energy range of 1-2 MeV for 10-18 MV X-ray beams, and are more hazardous than photons in causing radiation-induced late effects [ 6 ]. Neutrons have a radiation quality factor higher than radiation quality factor for photons. This quantity shows that the biological effects of neutrons are higher than those of photons. The quality factor for neutrons ranges from 1 to 20 [ 7 ].

Neutrons are sources of biological damage owing to their high radiation quality factor. The neutron dose received by the body leads to an increased risk of induction of secondary cancers outside the treatment region. There are many studies on the induction of secondary cancers following radiotherapy. For example Nyandoto et al., [ 8 ] stated in their study that during a follow-up consisting 4020 person-years, 27 patients developed secondary cancer. Kleinerman et al., [ 9 ] mentioned in their study that among the 49,828 women treated with radiation, 3750 cases survived 30 or more years and a two-fold risk of cancers of irradiated organs was seen. Anil et al., [ 10 ] stated in their study that cervical cancer patients treated with radiotherapy are at increased risk of second cancers at sites in close proximity to the cervix [ 11 ].

Owing to the importance of the neutrons produced, it is necessary that neutron doses be considered in radiotherapy treatment. Measuring the neutron dose in the patient’s body using neutron detectors is not easy. Therefore, the use of an accurate computational code is a useful tool to achieve this goal. Monte Carlo (MC) methods have been widely used in medical radiation physics, especially in radiation therapy physics. One of the most popular MC software packages that have been used in a large number of applications is the Monte Carlo N-Particle (MCNP) transport code package and the present study was performed using this package.

Several studies have been performed on the investigation of the effect of neutron doses to patients undergoing radiation therapy, and on neutron contamination dosimetry around high-energy linacs for different types and energies of linacs. Zabihinpoor et al., [ 12 ] in their study used Neptune accelerator to investigate neutrons. Their results indicate that when the distance from the isocenter decreases, production of photoneutrons will increase. And as the radiation field increases, neutron production increases.

Martinez et al., [ 13 ] calculated the neutron dose for 15 and 18 MV photon beam of Varian 2100C/D and 15 MV photon beam of Elekta linac. Their results show the amount of neutrons produced by 15 MV linacs is smaller than that found for the 18 MV linacs. Ma et al., [ 14 ] used MCNPX code for simulations. Simulations were performed for various field sizes which are most often used in radiation therapy.

In this study, a detailed geometry of 18 MV Siemens Primus Plus linear accelerator head was simulated using the Monte Carlo method. In this accelerator, the flattening filter which is made of stainless steel is more complex, and different from that which is used for the 6 MV. Due to the complex structure of the flattening filter, and due to different geometries of the jaws and various components of the Siemens Primus Plus accelerator, neutron production in this accelerator is different from other accelerators.

The aim of the present research is to study photoneutron production for the 18 MV photon beam and the effect of flattening filter on electron and photon spectrum for Siemens Primus Plus medical linear accelerator using MCNPX code. Several studies were performed on the neutron contamination around various linacs. These studies were performed with different computational codes [ 15 - 16 ].

Material and Methods

This study is an experimental study. Different components of the Siemens Primus Plus accelerator, with 18 MV photon beam, were considered for studying the production of neutrons in various fields. In the present study, contribution of the linac head components to photoneutron production, neutron source strength, and the effects of flattening filter on electron and photon spectra were calculated. The reason for calculation of the effect of flattening filter on photon and electron energy spectra is that neutron production is based on the interaction of electrons and photons with linac’s head components and patient’s body. When the photon and electron energy spectra change, the neutron production also changes. It is known that flattening filter absorbs photons and electrons and by removing flattening filter, photon and electron energy spectra are increased. For this reason, the photon and electron energy spectra were obtained on the phantom surface to determine that there are neutrons on the phantom surface. According to the photon and electron energy spectra, it can be seen that in high energy beams a number of peaks are observed (though negligible). These small photon and electron components can produce neutron which have destructive biological effects.

Simulation of Siemens Primus Plus linac

As the first step of the present study, a Siemens Primus Plus medical linac was simulated using MCNPX software (version 2.7.0). Validation of this model was performed in a previous study by Dowlatabadi et al, [ 17 ]. The Siemens Primus Plus medical linac has two treatment modes: photon and electron. This linac works with two photon energies (6 and 18 MV) and five electron energies (6, 8, 10, 12, 15 and 18 MeV) at the treatment center of this study. The geometric characteristics of the accelerator (composition and density) were provided by the linac’s manufacturer. The comparisons of dose profile and PDD (Percent Depth Dose) values obtained by MC simulations and measurements were performed by calculation of gamma function. For dose profiles and PDD data, the agreement was obtained between two sets of the data for 5 × 5 cm2, 10 × 10 cm2 and 20 × 20 cm2 field sizes. Dose profile in more than 90% of the points of the simulations had gamma values less than unity, and for PDD, nearly all data of the points of the simulations had gamma values less than unity. Gamma functions between zero and unity are considered as pass or agreement, while gamma values higher than unity are considered as fail or disagreement.

The geometry of the Siemens Primus Plus medical linac’s head is illustrated in Figure 1 and the material compositions of the simulated components of the linac’s head are tabulated in Table 1. The head of the linac contains the following components: target, absorber, flattening filter, primary collimator, photon monitoring chamber, mirror and jaws. The target has a cylindrical shape with a height of about 1.5 cm and a diameter of approximately 3 cm. The flattening filter is made of stainless steel and is located at a distance of 4 cm from the target. The primary collimator is made of tungsten and is located under the target at distance of 1.54 cm from the target, having a height of about 6.52 cm. In addition to the head components, a water phantom was simulated as well. A cubic water phantom with dimensions of 50 cm × 50 cm × 50 cm was simulated, the surface of which was 100 cm away from the target.

Figure 1

Schematic representation of the Siemens Primus Plus linac’s head geometry in the photon mode (Y-Z view). The water phantom was defined as a cube with dimensions of 50 cm × 50 cm × 50 cm.

Table 1

Materials of the various components in the 18 MV photon beam energy of the Siemens Primus Plus linac. The characteristics of the accelerator geometry were supplied by the manufacturer, Siemens.

Component	Material
Jaws	Tungsten
Mirror	Silicon oxide (SiO2)
Target	Gold
Absorber	Aluminum
Flattening filter	Stainless steel alloy (SST-303)
Primary collimator	Tungsten
Photon dose chamber	Aluminum oxide (Al2O3)

In order to reduce the time of calculations, energy cut-off was considered and other methods of variance reduction were not used. The energy cut-off for photons and electrons was set to 7 KeV. The importance of the particle in each volume is represented by the magnitude of importance (IMP). If a cell importance is set to zero for a particle, the importance for tracking that particle in that cell will be set to zero.

The cell importance for both electrons and photons was set as 100 for cells that are considered in the calculations. The MC simulations in the present study were run on a computer with an Intel(R) core™ i7 processor, 4.00 GHz, featuring a 64-bit operating system.

Benchmark comparison was performed by comparing the simulated PDD data for the 5 × 5 cm2, 10 × 10 cm2 and 20 × 20 cm2 field sizes with the corresponding measured data. In addition, the dose profile data for different depths and energies for the 5 × 5 cm2, 10 × 10 cm2 and 20 × 20 cm2 field sizes were compared with the corresponding measured data, as it was mentioned in the previous study by Dowlatabadi et al, [ 17 ].

The dose profiles showed good agreement with the measurement data for all depths. The configuration of the simulated dose profiles matched well with the measurement at the central areas of the dose profiles.

Contribution of the linac head components to photoneutron production

All the simulations in this section were performed for a 10× 10 cm2 field size. The main components that have contribution to production of photoneutrons in a linac’s head are those with high atomic numbers, including the target, primary collimator, flattening filter and jaws. Lead and tungsten are the main elements that produce photoneutrons in different medical linacs, because their cross-sections for (ɤ, n) reaction are high. The energy threshold of photoneutron production for tungsten and lead are 7.19 MeV and 6.74 MeV, respectively [ 7 ]. In this section of the study, calculation method of contribution of the linac head components to photoneutron production is expressed. In order to obtain the contribution of each component in production of neutrons, calculations were performed using three methods which are explained in the following and the results were compared together. After comparing, the best method with the least discrepancies was selected.

The first method: in this step the MPN card was considered to be zero for all the components except for the desired component (when MPN command is considered to be zero, production of neutrons in that component is not considered). Subsequently, after running the programs, the obtained values were divided to the total values (the total number of produced photoneutrons). In other words, the ratio of the number of neutrons produced from these components to the total number of neutrons produced from all parts of the head of the accelerator was then calculated. By this way, contributions of the linac’s head components in photoneutron production were obtained.

The second method: in this step each component, such as the jaws, flattening filter and primary collimator, were selected as a volume. The number of neutrons entering into the surfaces corresponding to the desired volumes was then subtracted from the number of neutrons exiting from the surfaces. F1 tally was used to calculate the number of particles entering each surface. However, since F1 tally gives the number of particles passing through the surface regardless of their direction, a “Cn” card was used to segment the exit directions of the particles from the desired level compared to the normal vector. With segmentation of the particle output angle in the range of 0° to 90°, and 90° to 180° compared to the normal vector, and by subtraction of the input and output values, the number of neutrons produced in the desired volume was obtained.

The third method: in this step of study to run the program, “primt table 140” card was used to account for neutron production. In the MCNP code, the primt table 140 card is used to obtain photoatomic activity of each nuclide in each cell.

Energy cut-off for electrons and photons was set to 7 keV. Additionally, to calculate the neutron contamination, the energy cut-off for photons and electrons was set to 7 MeV. In the MCNP code, PHYS, MPN and MX card are used to obtain neutron quantities. For this reason, in this study in order to account for neutron production from (ɤ, n) interactions, “PHYS”, “MPN”, and “MX” cards were used. The PHYS command is used to specify the energy cut-off and the physics treatments. Additionally, in this program, “MT” card was used to calculate thermal neutron scattering. In these simulations, the type A uncertainties were below 1.9%.

Effect of field size on photoneutrons production

Owing to the relatively large contribution of jaws to neutron production, it is necessary to question to what degree the size of the radiation field affects the production of neutrons. To answer this question, the amount of neutrons produced at the isocenter by interaction of photons with the jaws was calculated in separate programs for the 5 × 5 cm2, 10 × 10 cm2 and 20 × 20 cm2 field sizes. In this step, the PHYS, MPN and MX card were used.

Neutron source strength

One of the quantities that used to describe the production of neutrons in a linac is neutron source strength (neutron yield) which is represented by the Q quantity. The neutron source strength represents the number of neutrons produced per 1 Gy photon absorbed dose. To calculate this value, according to the method proposed by McGinley and Landry [ 18 ], a spherical surface with radius of 100 cm was considered while the center of the spherical surface was positioned on the target. The study by McGinley and Landry described a method to determine the total neutron fluence (n/cm2) per unit X-ray dose at isocenter produced by several different linacs. The total neutron fluence is given by the sum of the direct, scattered, and thermal neutron fluences. F1 and F6 scoring tallies were used to calculate the photoneutrons fluence and photon air kerma at the isocenter, respectively.

The neutron fluence from the accelerator at the isocenter in terms of Gy can be calculated from the following formula (according to IAEA SRS-47 report) (International Atomic Energy Agency Safety Reports Series) [ 19 , 20 ]:

(1)

In this formula a is the transmission factor for the head shielding (0.85 for tungsten and 1 for lead, we considered a=0.85 for simplicity), d is the distance from the target to the fluence-measuring point and Q is the neutron source strength. In this study, after running the program, contribution of the scattered and thermal neutron fluences was negligible, for this reason this part of fluences was neglected. According to the method proposed by McGinley and Landry, with using relationship (1) it is feasible to calculate the neutron source strength value for the 18 MV photon beam of the Siemens primus plus medical linac and the Q values for different linac models with different energies were reported.

Effect of flattening filter on electron and photon spectra

The reason for calculating the photon and electron spectrum in this section is to evaluate the influence of these spectra on the production of neutrons. By removing the flattening filter, the photon and electron spectra are changed. In this step of the study to run the program, photon and electron spectra were calculated at distance of 100 cm from the source on the surface of the phantom for two cases, with flattening filter and without flattening filter for the 18 MV photon beam. In this step of the study photon and electron spectra were scored for the 5 × 5 cm2, 10 × 10 cm2 and 20 × 20 cm2 field sizes.

To calculate the electron spectrum, cells were in the form of cylinders with thicknesses of 0.001 mm were selected on the surface of the phantom. In this step, the F4 tally and E4 card were used to calculate the numbers of electrons crossing the cell.

Results

The contribution of different components of the linac to the production of neutrons for the 10 × 10 cm2 field is shown in Figure 2 and it is compared with other Siemens accelerators. In order to obtain the contribution of each component in production of neutrons, calculations were performed using the three mentioned methods and were compared together.

Figure 2

Neutron contribution (%) for various components of the Siemens Primus Plus accelerator (18 MV photon beam).

After the comparison, the best method with the least discrepancy was selected. In these calculations, the maximum statistical type an uncertainty in the MC calculations for the first, second and third methods were 1.1%, 1.9% and 0.64%, respectively. Among the three suggested methods, according to the results obtained in the output results of the program, the lowest statistical uncertainty of third method indicates the fine accuracy of this method. According to the data in Figure 2, the primary collimator has the largest contribution to production of neutrons, such that 59% of the total number of neutrons is produced by interaction of photons in the primary collimator. This result may be reasonable, because the primary collimator is made of tungsten. Tungsten has the lowest threshold energy in comparison to the other substances in the head of the accelerator for photonuclear reaction.

It can be seen from these results that, after the primary collimator, the largest contribution to production of photoneutrons is related to the jaws with a value of 25.5%. In most medical linear accelerators, the jaws are made of tungsten. Therefore, they are important components in production of neutrons and become the main sources of neutron production.

The high energy photons pass through the flattening filter, and we expect that the flattening filter has a greater contribution to producing neutrons but the results are opposite and contribution to producing neutrons is negligible. According to Figure 2, the contribution of the flattening filter to production of neutrons is 3.01%. The reason for this low contribution is the dominance of lighter elements, such as carbon, manganese, silicon, chromium, nickel, and iron in the flattening filter, that have higher energy thresholds for photonuclear interaction. The primary collimator and jaws are significant sources of neutrons.

The contribution of the jaws to production of neutrons for various radiation field sizes is listed in Table 2. It can be seen from the table that, by increasing the radiation field size, the contribution of the jaws to production of neutrons decreases. The reason for this trend is that, by increasing the field size, the opening angle of the jaws increases. Therefore, less material is placed in the path of the photon beam. For this reason, the number of photon interactions with tungsten in the jaws is reduced and the number of neutrons produced becomes lower. Mesbahi et al., [ 15 ], using a simulation of Varian accelerator (18 MV photon beam), evaluated the effect of field size on production of neutrons. Their study showed that with increasing field size, the neutron fluence decreases.

Table 2

Percentage value (%) of neutron production from the jaws of the Siemens Primus Plus medical linac for different field sizes.

	5 × 5 cm2	10 × 10 cm2	20 × 20 cm2
Neutron production in jaws (%)	26.82% ± 0.05	25.51% ± 0.02	22.01% ± 0.03

Discussion

The results of this study on the contribution of linac components are compared with the other models of Siemens linac in Table 3 [ 7 , 16 ]. MC calculations for the component contributions to photoneutrons for Varian 2100C/2300C medical linear accelerator are listed in Table 4 [ 19 ]. According to Tables 3 and 4, the differences between the data of these accelerators are due to different material compositions in the heads of these linacs. By comparing Siemens Primus Plus (18 MV photon beam) and Varian 2100C/2300C linac (18 MV photon beam), it is seen that the percentage contribution of each component to the production of photoneutrons for both linac is quite different. Differences between the data of these accelerators with 18 MV photon beams are due to different material compositions in the heads of these linacs. In the Varian accelerator, the flattening filter is made of tungsten but in the Siemens accelerator the flattening filter is made of stainless steel.

Table 3

Percentage (%) contribution of each component to the production of photoneutrons for the Siemens Primus Plus medical linac (15 MV and 18 MV photon beams).

Component	Siemens Primus (15 MV [7]) (%)	Siemens Primus (15 MV [16]) (%)	Siemens Primus Plus (18 MV) (This study) (%)
Target	10.08 (Au)	12.43 (Au)	12.33 (Au)
Primary collimator	54.85 (W )	52.29 (W)	59.01 (W)
Flattening filter	1.74 (SST )	0.41 (SST)	3.01 (SST)
Jaws	26.72 (W)	21.14 (W)	25.51 (W)
Absorber	0.01 (Al)	0.00 (Al)	0.13 (Al)
Others	6.6	13.73	0.01
Total	100	100	100

Table 4

Percentage (%) contribution of each component to the production of photoneutrons for the Varian 2100C/2300C linac.

Component	Varian (10 MV [3, 19]) (%)	Varian (15 MV [3, 19]) (%)	Varian (20 MV [3, 19]) (%)	Varian (18 MV [3, 19]) (%)	Varian (15 MV [19]) (%)
Target	0.013 (Cu)	9.2 (W,Cu)	17.1 (W,Cu)	15.5 (W,Cu)	9.0 (W,Cu)
Primary	44.2 (W)	38 (W)	35.5 (W)	39.9 (W)	38.0 (W)
collimator	0.034 (Cu)	22.4 (W)	10.3 (Fe,Ta)	9 (Fe,Ta)	24.3 (W)
Flattening filter	54.7 (W)	29.1 (W)	36 (W)	34.2 (W)	22 (W)
Jaws	1	1.3	1.1	1.4	5.2
Others	0.0	0.08	0.0	0.0	1.5
Total	100	100	100	100	100

The reason for the differences in the neutron contribution of the target is the low threshold energy for tungsten compared to copper and aluminum. Additionally, for the jaws and primary collimator, the reason for the differences in the contribution of neutrons is the low threshold energy of lead compared to tungsten. The flattening filter in the Siemens Primus Plus, owing to the low atomic number and high threshold energy, has a smaller contribution to the production of neutrons compared to the production of neutrons from other accelerators.

The results of different studies on neutron source strengths of various linacs are listed in Table 5. It can be seen from the table that, with increasing photon energy, the neutron source strength increases. In other words, the neutron strength for different linacs depends on the photon energy and the linacs’ head structures and the linacs’ model. For the Varian linac, the neutron strength increases significantly from 10 MeV to 18 MeV, and it reaches from 0.059 × 1012 neutron per Gy to 2.9 × 1012 at the isocenter. For the Siemens primus plus linac the neutron strength increases significantly from 15 MeV to 20 MeV, and it reaches from 0.2 × 1012 neutron per Gy to 0.92 × 1012 at the isocenter.

Table 5

Comparison of the neutron source strength (neutron Gy-1) of various medical linacs.

Manufacturer	Model	Energy (MV)	Q (neutron Gy−1)	Reference
Siemens	Primus plus	18	0.83×1012	This study
Siemens	Primus	20	0.92×1012	Naseri and Mesbahi [3]
Siemens	Primus	15	0.17×1012	Pena et al [16]
Siemens	Primus	20	0.92×1012	McCall [21,22]
Siemens	Primus	15	0.20×1012	Lin et al [23]
Siemens	Primus	15	0.136×1012	Becker et al [24]
Siemens	Primus	18	0.88×1012	Followill et al [25]
Siemens	Primus	15	0.2×1012	Followill et al [25]
Siemens	Primus	15	0.2×1012	Mohammadi et al [26]
Varian	1800C	18	2.27×1012	McGinley and Landry [18]
Varian	1800C	15	1.23×1012	McGinley and Landry [18]
Varian	1800C	10	0.06×1012	McGinley and Landry [18]
Varian	1800C	18	2.9×1012	McCall [22]
Varian	20C	15	0.93×1012	McCall [22]
Varian	18C	10	0.059×1012	McCall [22]

The photon and electron spectra at distance of 100 cm from the source on the surface of the phantom were scored for the 5 × 5 cm2, 10 × 10 cm2 and 20 × 20 cm2 field sizes. The photon energy spectrum for the two cases, with flattening filter and without flattening filter in 18 MV photon beam, on the phantom surface for the 5 × 5 cm2, 10 × 10 cm2 and 20 × 20 cm2 field sizes are shown in Figure 3. In this diagram, the photon fluence is higher for the non-filter case for all the three field sizes. Based on this diagram, the photon fluence per incident electron for the non-filter case are 4.62, 2.93 and 2.79 times compared to the with flattening filter case for the 5 × 5 cm2, 10 × 10 cm2 and 20 × 20 cm2 field sizes, respectively.

Figure 3

Photon energy spectra for with filter and non-filter case 18 MV photon beam on the phantom surface for different field sizes: (a) 5 × 5 cm2, (b) 10 × 10 cm2 and (c) 20 × 20 cm2.

It can be seen that, as the field size decreases, the photon fluence increases for the non-filter case in comparison to the flattening filter case. When the field size increases, more photons are crossed within the flattening filter and the ratio of the photon fluence for the non- flattening filter case compared with the flattening filter case is decreased. From Figure 3, it can be seen that the ratio of the photon fluence for the non-filter case in comparison to the flattening filter case decreases from 8.62 to 4.62 with the increase in the field size from 5 × 5 cm2 to 20 × 20 cm2, respectively.

The electron energy spectrum on the surface of the phantom for the 5 × 5 cm2, 10 × 10 cm2 and 20 × 20 cm2 field sizes is shown in Figure 4 (for the non-flattening filter case and with flattening filter case). The electron fluences for the non-flattening filter case are 4.62, 2.93, and 2.79 times compared to the flattening filter case for the 5 × 5 cm2, 10 × 10 cm2 and 20 × 20 cm2 field sizes, respectively. It can be mentioned that, with decreasing field size, the electron fluence increases for the non-flattening filter case analogously to the flattening filter case. These findings are in close agreement with those reported by Mesbahi et al., [ 15 ] and Kry et al, [ 21 ].

Figure 4

Electron energy spectra for with filter and non-filter case 18 MV photon beam on the phantom surface for different field sizes: (a) for 5 × 5 cm2, (b) for 10 × 10 cm2 and (c) for 20 × 20 cm2.

Conclusion

The photoneutron production in the Siemens Primus Plus medical linac (18 MV photon beam) in a 10 × 10 cm2 field was calculated and presented. When the field size increased, the photoneutron production is decreased. When the field size increases from 5 × 5 cm2 to 20 × 20 cm2, a 17.93 % decrease in the photoneutron production was seen.

The neutron source strength depends on the accelerator model, field size, photon energy, geometry of the simulation and the computational code. The results show that, with increasing field size, the neutron production from jaw was reduced. The reason for this trend is that, by increasing the radiation field, the jaws’ opening angle increases and, therefore, less material is located in the path of the photons. For this reason, the number of photon interactions with tungsten inside the jaws decreases and the number of neutrons produced is lower.

The data of neutron source strength in Table 5 are a part of all the published Q values to date. This data will facilitate physicists to accomplish shielding calculations and with this data, physicists can have a better choice in the preparation of accelerators. According to the data in Table 5, neutron production in the Siemens Primus Plus medical linac’s head is lower than other accelerators and its usage is recommended.