Introduction
The greater dosimetric accuracy and geometrical precision are required to deliver a very high dose of radiation during stereotactic radiosurgery (SRS). The conical cone collimator (CCC) is a tertiary collimator that usually provides a small circular opening of 4 mm to 20 mm diameter defined at the isocentre. CCC has become predominantly used for SRS in the treatment of brain tumours like arteriovenous malformation, trigeminal neuralgia, acoustic neuroma and pituitary tumours. Reference Tuleasca, Regis and Sahgal1,Reference Gevaert, Levivier and Lacornerie2 CCC offers a smaller penumbra, sharper dose fall-off, higher mechanical stability and lower transmission than multi-leaf collimator (MLC). However, small-field radiation dosimetry is itself challenging due to the lack of electronic equilibrium, detector size, steep dose gradient, partial volume averaging effect and occlusion of the radiation source. Besides this, the beam data required for the commissioning of SRS cone demand higher dosimetric and geometrical accuracy. Several studies have reported 10% uncertainty in the measurement of small-field dosimetric data below 10 mm. Reference Benedict, Yenice and Followill3 The most critical parameter is the output factor (OF) which is very sensitive to field size, detector type and positioning of the detector. Reference Benedict, Yenice and Followill3,4 The independent validation of these experimental data is essential during the commissioning of CCC for SRS before clinical use.
The techniques of Monte Carlo (MC) are well-established in the field of medical radiation physics. The MC techniques are recognized as the most accurate ways for predicting the dose during radiation transport with minimum uncertainties. Reference Rogers, Faddegon, Ding, Ma, We and Mackie5 CCC offers a small circular field that has difficulties in establishing electronic equilibrium where larger dosimetric uncertainties are involved. The MC technique is well known for obtaining an accurate dose distribution in a small field by accounting for the loss of electronic equilibrium, dose from buildup region and backscatter. MC has been widely used for the commissioning and clinical validation of photon and electron beams. The MC simulation technique provides an independent and highly accurate way of predicting absorbed dose distribution in diverse geometries. Numerous studies have availed the MC simulation technique for dosimetric evaluation of CCC from different vendors. Reference Cheng, Ning, Arora, Zhuge and Miller6–Reference Huang, Morales, Butson, Johnson, Butson and Hill9 The works published by Cheng et al. Reference Cheng, Ning, Arora, Zhuge and Miller6 are the well-known set of data published related to the dosimetry of the SRS cone for 6MV flattening filter-free (FFF) beam from Varian. However, Cheng et al. work is limited to the comparison of simulated and measured output cone factors.
There have been many publications reporting experimental data on the SRS commissioning of different medical linear accelerators (Linac) with micro MLC and CCC. Reference Belec, Patrocinio and Verhaegen10–Reference Hermida-López, Sánchez-Artuñedo, Rodríguez and Brualla14 However, there is a wide variety of available literature that is very much diversified and differentiated based on different aspects of SRS commissioning. This makes it very difficult to establish comparisons between the present set of data. The authors Gocha Khelashvili et al. (2011), Marcelino Hermida-Lopez et al. (2012) and Wiant D B et al. (2013) Reference Belec, Patrocinio and Verhaegen10,Reference Hermida-López, Sánchez-Artuñedo, Rodríguez and Brualla14,Reference Wiant, Terrell, Maurer, Yount and Sintay15 reported most of the experimental data on SRS commissioning using the Brain lab stereotactic cone. However, very limited literature is available on the full-fledged commissioning of SRS eclipse cones from Varian Medical System with limited cone sizes. This study aims at obtaining the beam data required for the commissioning of CCC on a Truebeam linac for 6 MV FFF beam. The study also demonstrates the most comprehensive dosimetric beam parameters of eclipse cone commissioning and validation of experimental data for a 6 MV FFF from Truebeam linac based on the MC approach. Previous studies have validated geometrical modelling and MC simulation of 6 MV FFF from Truebeam linac. Reference Shende, Dhoble and Gupta16 The present study is carried out as specific beam data essential for commissioning of the cone dose calculation (CDC) algorithm in eclipse cone treatment planning system (TPS).
Methods & Materials
The geometrical source modelling of the TrueBeam linac was built using PRIMO version 0·3·64·1814 (https://www.primoproject.net) simulation software under fake beam geometry. Reference Rodriguez, Sempau and Brualla17 Here, the study was aimed at MC simulation of CCC and analysing dosimetric characteristics for the SRS eclipse cone manufactured by Varian Medical System (Inc., Palo Alto, CA, USA) for 6 MV FFF Truebeam linac. The CCC acts as a tertiary collimator attached at end below the secondary collimator of linac. All the experimental measurements for CCC were carried out using an EDGE diode detector in a 3D SunScan water scanning system from Sun Nuclear, Melbourne, USA. EDGE detector with a sensitive volume of 0·019 mm3 and sensitive area of 0·8 × 0·8 mm2 was used to measure experimental beam data. Besides, the SNC0125c ionization chamber of volume 0·125 cc was used as an intermediate chamber for correcting OFs. The percentage depth dose (PDD), tissue maximum ratios (TMRs), lateral dose profiles (LDPs), and OFs were measured to configure the CDC algorithm for the Varian eclipse cone of diameter 5 mm, 7·5 mm, 10 mm, 12·5 mm, 15 mm, 17·5 mm and validated against MC-simulated beam data. All the experimental measurements were performed to match the commissioning requirements of the eclipse cone beam configuration in TPS. The recommended secondary collimator jaw (X and Y jaw) setting was kept at 5 × 5 cm2 for beam data measurement of all the cone sizes. The recommendations of TRS-483 were followed during data measurements for the commissioning of SRS cones. The beam data required to commission the CDC algorithm for above mentioned cones were validated against MC using PRIMO.
PRIMO Monte Carlo simulation
PRIMO is free, non-open source software based on MC general purpose radiation transport code PENELOPE 2011 Salvat et al. for calculation of absorbed dose distribution. Reference Salvat, Fernandez-Varea and Sempau18 PRIMO uses the PENEASY/PENEOPE MC code to simulate Electro-Magnetic (EM) showers in segment-1. PENNELOPE simulates the combined transport of photons, electrons, positrons and their interaction scheme categorized into soft and hard collisions. PENELOPE needs a definite set of simulation parameters under the transport parameter configuration. Reference Brualla, Rodríguez and Sempau19 The default set of parameters used in PRIMO are C1: average angular deflection between consecutive hard collisions, C2: maximum average fractional energy loss between hard collisions, WCC: energy cut-off between hard and soft collisions, WCR: bremsstrahlung energy cut-off, dsMax: maximum allowed step length for charged particles; and EAbs: terminal absorption energies. The transport parameters used during the simulation were as, C1 = C2 = 0·1, WCC = 200 KeV, WCR = 50 KeV. The cut-off energies for electron, positron and photon were set at Eabs(e−) = Eabs(e+) = 200 KeV and Eabs (ph) = 50 KeV. PRIMO simulates the patient’s independent and dependent parts of linac performed under segments S1, S2 and S3. Segment S1 allows tallying or producing phase-space file (PSF) at the downstream end of the upper part of linac. Similarly, segment S2 includes PSF tallied or produced at the downstream end of the lower part of linac. At the end, the estimation of absorbed dose distribution in water phantom or CT is included in segment S3. The PSF generated at the end of segment S1 for the upper part of linac during the previous study was used for geometrical source modelling of 6 MV FFF beam from Varian Truebeam linac. Reference Shende, Dhoble and Gupta16 Subsequently the simulation of eclipse cones was performed in segment S2. The total numbers of 5 x 108 primary particle histories were simulated in S1, which produced a PSF file of 100 gigabytes in size. The simulations of each cone were performed individually during the simulation of segments (S2 + S3) attached at the downstream end of the linac. The initial beam parameters used in modelling of 6 MV FFF beam were initial beam energy, full-width half maxima (FWHM) of energy, FWHM of the focal spot and beam divergence given as 5·85 MeV, 0·05 MeV, 0·8 mm and 0·05 degree, respectively. Absorbed dose distributions were tallied within a slab water phantom of dimension 25 cm × 25 cm × 25 cm with a dose scoring voxel of size x = 0·1 cm, y = 0·1 cm, z = 0·1 cm. The measure of performance of calculations is nothing but computational efficiency (η), which depends on calculation time (T) and variance (σ2). PRIMO introduced the variance reduction technique (VRT) and interaction-forcing factor to increase calculation efficiency. PRIMO recommends Russian roulette splitting as a VRT technique. A higher interaction-forcing factor increases simulation time which consequently reduces the computational efficiency chosen close to 16. The computed tomography (CT) factor recognized as particle splitting in phantom was kept at 100 during MC simulation.
SRS cone simulation
The SRS cone is a cylindrical tertiary collimator accessory hooked below the secondary collimator. PRIMO allows us to simulate the physical properties of the cone in the segment S2. The distance between the source to bottom of the CCC in a Truebeam linac is fixed at 74 cm. The MC simulations were carried out for a source to CCC distance of 63 cm, physical length of CCC 11 cm and its nominal aperture size at the isocentre. The cones of various diameters ranging from 5 mm to 17·5 mm with an increment of 2·5 mm were simulated. The corresponding PSF generated at the end of the cone was restored in segment S2. PRIMO uses this PSF in its next subsequent segment S3 for final dose computation in water phantom or CT of interest. Table 1 shows the PENELOPE radiation transport parameter used in PRIMO.
Final initial beam parameters used for MC simulation of 6MVFFF nominal beam energy with conical cone collimator for Truebeam linac in PRIMO
PDD and LDP
PDD is defined as the absorbed dose at any depth d to absorbed dose at the reference depth of dose maxima. Reference Khan21 The mathematical expression for PDD is written as follows.
$$PDD = {{{D_d}} \over {{D_{ref}}}}*100{\mkern 1mu} \% $$
where Dd is the dose at any depth and Dref is the dose at reference depth. Dref can be the depth of dose maxima. MC simulations of all the cones were performed to obtain simulated PDDs and LDPs in PRIMO. The LDPs are also referred to as off-axis ratios (OARs). Likewise, both sets of PDDs and profiles were measured experimentally using a computer-controlled Radiation 3D-SunScan Field Analyzer (RFA) from Sun Nuclear. These measurements are sensitive to detector position and require detector centring. Therefore, before acquiring the actual depth dose scan centring of the radiation beam axis, the vertical alignment of the cone and detector positioning was verified by using the ray-trace method. This ensures the detector follows the beam centre, which is essential in a small-field depth dose scan. The diameter of a 15 mm cone was used during ray tracing, where LDPs were acquired at depths of 5 cm and 20 cm to determine central beam alignment. The beam central alignment correction was applied for all depth dose scans. In addition, the centring of both profiles was done by central axis correction. The PDD curves were obtained in step-by-step scanning mode with an increment of 1 mm, whereas continuous mode was used to measure dose profiles. All the cone PDDs were simulated and measured at 100 cm SSD and normalized to 100 % at the depth of dose maxima (D max ). Similarly, profiles were measured and simulated at a depth of 5 cm for three different source-to-surface distances (SSD) 80 cm, 90 cm and 100 cm normalized to 100% at the central axis. To analyse the measured PDD and profile curves, they were converted to.dat* files and imported into the PRIMO workstation. Those sets of data were analysed using the gamma index evaluation tool incorporated in PRIMO as presented by Low et al. Reference Low, Harms, Mutic and Purdy20 Both simulated and measured PDDs and profiles were evaluated based on the gamma analysis index (ϒ) that quantifies the level of agreement or disagreement between measured and MC-simulated curves using gamma-passing criteria of ϒ2%/1mm where, (2 % dose difference (% DD) and 1 mm distance to agreement (DTA)) with a minimum passing rate of 95 %. The gamma analysis of dose distribution was performed globally for absolute dose verification. The estimated ϒ2%/1mm ≤ 1 and ϒ2%/1mm > 1 are considered criteria for passing and failing, respectively.
Tissue maximum ratio (TMR)
The TMR is defined as the ratio of the dose rate at a given point in the phantom to the dose rate at the same point for reference depth of dose maxima. Reference Khan21 The mathematical expression for TMR can be written as,
$$TMR = {{{{({D_d})}_p}} \over {{{({D_{\max }})}_p}}}*100{\mkern 1mu} \% $$
where (D d ) p is dose at depth d at point p and (D max ) p dose at depth of dose maxima at same point p. TMR and PPD are interrelated by a classical equation derived by Khan et al. Reference Khan21
$$TMR(d,rd) = {{P{{(d,r,SSD)}_{}}} \over {100}}*{\left( {{{SSD + d} \over {SSD + {d_{\max }}}}} \right)^2}*\left( {{{{S_p}({r_{d\max }})} \over {{S_p}({r_d})}}} \right)$$
where P is PDD, d is depth, d max is the reference depth of dose maxima, r is the cone field size and S p is the phantom scatter. The commissioning of cone beam planning needs TMR is a basic requisite for the commissioning of the CDC algorithm in TPS. TMRs were measured directly using a computer-controlled SunScan 3D water phantom (RFA). TMRs were acquired for the range of all cone sizes at a source-detector distance of 100 cm. To reduce spikes in the measurements, TMRs were measured in water-draining mode instead of water-filling mode. However, MC-simulated TMRs were indirectly determined by converting MC-simulated PDDs. Reference Battum, Essers and Storchi22 All the TMR curves were normalized to 100 at Dmax, and simulated TMR curves were compared against the measured TMR.
Cone OFs
The OF is defined as the ratio of output for a given field size to the reference field size at a specific point in the water phantom under maximum scatter conditions. Reference Khan21 The mathematical expression for the relative OF can be given as,
$$OF = {{D{{(r,{\mkern 1mu} {\mkern 1mu} {d_{}})}_{}}} \over {D({r_{ref}},d)}}$$
where D(r, d) is dose for a field at depth d and D(r ref , d) is dose for reference field at same depth d. The OFs were measured at a depth of 5 cm for source-to-phantom distance (SPD) at 95 cm and source-to-axis distance (SAD) at 100 cm in an isocentric setup. Similarly, OFs were estimated for the same field geometry arrangement using the MC simulation approach in PRIMO. All the measured OFs were corrected for their limitations in small-field dosimetry. For this, the small-field detector (SFD) was cross-calibrated using the cylindrical chamber SNC0125c at an intermediate open field of 3 × 3 cm2 known as intermediate daisy-chain method. 23 OFs were normalized for an open reference field size of 10 × 10 cm2. The corrected OFs were determined as follows,
$$O{F_{Corr.}} = {{SF{D_{(Cone)}}} \over {SF{D_{(3x3)}}}}*{{CC{{0125}_{c(3x3)}}} \over {CC{{0125}_{c(10x10)}}}}$$
where SFD (Cone) is EDGE diode reading for various cone sizes. SFD (3 × 3) is for diode open field reading. Similarly, CC0125 c(3 × 3) and CC0125 c(10 × 10) are the reading for open fields using SNC0125c. The dose output for all the cones and the reference field size were determined using MC simulation. PRIMO-simulated OFs were validated against experimentally measured OFs.
CDC algorithm and absolute dose measurement
The CDC algorithm has been employed in eclipse cone planning to calculate the dose for stereotactic cone collimator in the treatment of SRS. CDC uses TMR, OAR and cone OFs to determine dose at any point within the volume. CDC calculates the dose at any arbitrary point is given by,
$$\eqalign{ & D(r,d,SSD,S) = MU*D{R_{ref}}*O{F_{TMR}}(s)*TMR(d,s) \cr & \quad \quad \;\quad \quad \quad \;\quad \;\;*{\left( {{{SAD} \over {SSD + d}}} \right)^2}*OAR(r,s) \cr} $$
where
D(r, d, SSD, S) = Dose at location of interest, MU = Delivered monitor unit,
DR ref = Reference Dose rate, OF = Output Factors,
TMR(d, s) = Tissue Maximum Ratio, OAR(r, s) = Off-Axis Ratio,
r is off-axis distance, d is the depth of point of interest along the central axis, and S is nominal diameter of the conical collimator. However, the CDC has its limitations such as the approximation of an arc beam as a static beam, the absence of backscatter near the cavities and exit of the beam, ignoring tissue inhomogeneity and obliquity of beam entry. CDC requires absolute dose measurement in beam configurations measured at a depth of 5 cm for a reference field size of 10 × 10 cm2 and SPD 95 cm. The absolute dose measurement was simulated under the same reference geometry setting in PRIMO.
Results
The experimental beam data acquired for various cones of 5 mm, 7·5 mm, 10 mm, 12·5 mm, 15 mm and 17·5 mm were validated using MC. The initial beam parameters obtained iteratively that truly exhibit characteristics of our existing Truebeam linac are shown in Table 1. The experimentally measured and MC absolute dose obtained at a depth of 5 cm for SSD 95 cm were matched within 0·5 % showing excellent agreement. The maximum statistical uncertainties during the MC simulation estimated at the end of segment S3 were found to be 0·64%.
MC validation of PDD & TMR
Figures 1 and 2 compare the measured and MC-simulated PDDs and TMRs curves for conical cone beams of various cone sizes, respectively. The misalignment of the cone and detector along the central axis was found to be 0·03° to the extent of 20 cm depth. This central axis offset error was corrected using the ray-trace method for all depth dose scans. Table 2 summarizes the depth dose values for measured and simulated PDDs and TMRs. Both sets of measured and simulated PDD and TMR curves for all the cones are nicely superimposed on each other except for the smallest cone of 5 mm diameter shown in Figs. 1 and 2, respectively. The result shows the maximum deviation between measured and simulated PDDs or TMRs were within 3% except for cone of 5 mm diameter. The difference between measured and simulated PDDs or TMRs at depths of 10 cm, 20 cm and at range of 50 % dose was substantially higher for diameters of smaller cone sizes. The maximum deviation in PDDs and TMRs at depths of 10 cm, 20 cm and at range of 50% dose was found 4·05 %, 7·52 %, 5·52 % and 4·04 %, 7·03 %, 5·23 %, respectively, for the cone of 5 mm diameter. Close agreements were seen between values of measured and simulated depth of dose maxima (d max ) and ratio of PDDs at 20 cm and 10 cm depth (PDD20/10). The differences between measured and simulated values of d max were found below 0·1 mm as shown in Table 3. The ratio of PDD20/10 for the measured and its corresponding simulated PDDs were found 0·49 ± 0·01 and 0·5 ± 0·01 over the range of dimensions for various cone sizes. The result of gamma analysis shows close agreement between the dose distribution obtained for measured and simulated depth dose curves. The average gamma index before and after dose maxima were found ϒ2%/1mm ≤ 1 with a minimum percentage of point passing ≥ 98·78 % for all the cones. The gamma analysis results for ϒ2%/1mm also show maximum deviation in % DD, and DTA were observed for 5 mm cone at a depth of 10 cm shown in Table 3.
Comparison of measured and MC-simulated PDD curves for conical cone collimator of different diameters.
Comparison of measured and MC-simulated TMR curves for conical cone collimator of different diameters.
MC-simulated PDD and TMR versus experimentally measured PDD and TMR for cones of different sizes
Note: All the *TMR values are multiplied by 100.
Gamma analysis of measured and MC-simulated PDD curves for different cone sizes
MC validation of LDPs
The comparisons of measured and MC-simulated LDPs obtained for the diameter of different conical cones are shown in Fig. 3. This shows LDPs (cross-line and in-line) measured at a depth of 5 cm for cones of different diameters at three different SSDs. The values of FWHM represent the size of the conical cone estimated from measured, and MC-simulated profiles are within ± 0·2 mm summarized in Table 4. However, percentage doses obtained at values of FWHM exhibit good agreement between measured and MC-calculated doses below 3 % for the diameter of all cones except for the 5 mm cone. Table 5 summarizes the results for variation of measured and MC-simulated percentage dose profiles compared at 80 %, 50 % and 20 % doses for depth of 5 cm and SSD 100 cm. This deviation in percentage dose difference (% DD) and relative distances (RD) were found substantially higher in the penumbra region around 80 % and 20 % dose profiles for all cones. The greatest difference between measured and MC values of % DD or RDs in the penumbra region of dose profiles over all the cones was found below ± 15·5 % and 1 mm, respectively. However, % DDs and RDs in the region of 50 % dose profiles (central region) were found below ± 2·5 % and 0·11 mm except for 5 mm cone. The penumbra region in the measured dose profiles was found to have a steeper descent compared to MC-simulated profiles. The penumbra for measured and MC dose profiles varies from 1-to-2·5 mm and 1·5-to-3·5 mm over all cone sizes, respectively. The maximum disagreement between the penumbra of measured and MC dose profiles was found below 1·5 mm over all the cone sizes. Table 6 summarized gamma-passing results for measured, and MC LDPs acquired at a depth of 5 cm and SSD 100 cm were analysed using ϒ2%/1mm criteria. The maximum average gamma index inside, outside and in the penumbra regions, was within 0·51, 0·18 and 0·68 with a minimum percentage of ϒ2%/1mm passing rate ≥ 97·6 % respectively, for both transverse and longitudinal profiles. This indicates overall agreement between measured and MC dose profiles.
Comparison of measured and MC-simulated lateral dose profiles for conical cone collimator of different diameters.
FWHM of simulated and measured depth dose profiles at 5 cm depth for SSD 100 cm
Comparison of measured and MC-simulated depth dose profiles at 5 cm depth for SSD 100 cm
Note: Lt. = Left side % dose difference (% DD), Rt. = Right side % dose difference (% DD), Δ = Relative Distance (mm).
Gamma analysis of measured and MC-simulated depth dose profiles at 5 cm depth and 100 cm SSD for various cone sizes
Cone OFs
Table 7 summarizes measured and simulated OFs for circular fields of various cone sizes. The OFs measured using an EDGE diode detector corrected with an intermediate field were compared against the MC-simulated OFs. OFs are functions of cone diameters, which increase with the cone size. The variation of measured and simulated OFs together with Varian recommended OFs as a function of cone diameter are plotted in Fig. 4. This shows the difference between measured and MC-simulated OFs is consistently increasing as size of the cone reduces. The measured OFs are consistently larger than the MC-simulated using PRIMO. The Varian OFs agreed very well with the measured OFs. However, simulated OFs showed more deviation than measured ones as the cone size gets smaller. The maximum deviation of 4·78 % was observed between simulated and measured OFs for the smallest cone of 5 mm diameter. These differences between OFs for cones greater than 10 mm were found to be below 3 %. The OFs for cone diameters of 15 mm and higher are perfectly matched below 0·5%.
Comparison of measured and MC estimated output factors
Comparison of measured and MC-simulated output factors for conical cone collimator of different diameters.
Discussion
The MC model of the Varian conical cone for the 6 MV FFF beam from Truebeam linac was presented and its dosimetric validation of SRS eclipse cone beam data (PDDs, TMRs, LDP and OFs) has been performed using MC simulation. The measured and simulated PDDs or TMRs are in good agreement with each other except for a cone of 5 mm diameter. The PDDs, TMRs and Dmax are functions of cone size that increase as cone size increases as would be expected. Reference Palta, Rogers and Cygler24 Both the measured and MC PDDs or TMRs curves for cones of 10 mm or higher are closely overlaid within 1·5 %. However, significant divergence is seen below 10 mm for 7·5 mm and 5 mm cones at higher depth. Smaller cones have a greater tendency to be misaligned with the beam’s central axis and detector. A slight misalignment of the cone and detector central axis could result in a larger dose variation. From Figs. 1 and 2 one can appreciate that measured PDD curves exhibit slightly low doses, which could be the result of the small electron range in diode material and volume averaging response of diode detector at the small field for low-energy photons relative to MC. Reference Khelashvili, Chu, Diaz and Turian7 The experimentally measured TMRs were compared against TMRs converted from MC PDDs, because PRIMO does not provide MC-simulated TMRs directly. Both measured and MC TMR curves are nicely superimposed on each other except for the 5 mm cone. Diode detectors have their own issues associated with dose rate, energy and directional dependence. In addition, as the size of the beam gets smaller and narrower, electronic equilibrium tends to decrease. The contributions of those effects are primarily observed in the smallest cone of 5 mm diameter as can be seen in Figs. 1 and 2. The accuracy of simulated PDDs or profiles also depends on the number of particle histories and typical voxel size. As PENELOPE allows only a fixed number of voxel 108 in S3 simulations, it limits the size of voxel results in averaging of dose. The maximum statistical uncertainties in the measurement were 0·64 %.
The comparisons of measured and MC-simulated LDPs also referred as OARs are the function of off-axis distance for a cone of different diameters at different SSD as shown in Fig. 3. This also demonstrates that the widening of the profile increases with an increase in SSD caused by beam divergence. The resultant average gamma index and percentage of gamma passing for the comparison of measured and MC profiles summarized in Table 7 indicate close agreements between them. The measured FWHM is a characteristic of the physical dimension of the cone that agrees with MC’s estimated FWHM within ± 0·2 mm. The disagreement between the measured and MC dose at the point of FWHM was found below 3 % except for the 5 mm cone. The difference between measured and MC doses at FWHM found to be increase as the size of the cone decreased. The FWHM of the beam profile lies in the high dose gradient region which makes it highly sensitive to detector position. The lateral distance between 80% and 20% of dose profiles gives penumbra indicating steepness of descent of the curves increases with cone size can appreciated from Fig. 3. The doses in the penumbra region around 80 % of dose profiles are substantially higher in experimentally measured profiles relative to MC. However, measured doses around 20 % region and beyond are found to be significantly lower compared to MC. The response function of the diode detector depends on the sensitive region of the detector, and EDGE diodes have a sensitive region of 0·8 mm. The region of 80 % dose profile that slightly diverges from the centre relative to the MC profile could be due to over-response of the detector for low-energy photons within the field. Its prominent impact could have been seen in the 5 mm cone, where the measured profile completely encompassed within MC profile. However, dose at 20 % of the profile little converges towards the centre relative to MC. This might be the effect of the small electron range and insufficiency of the diode detector to account for transmission of the beam due to the bottom end of the cone in region 20 % of dose profile and beyond it. However, MC takes into account dose precisely in the low-dose region beyond the penumbra and the range of electrons outside the field. In addition, dose along LDPs are greatly influenced by dose averaging effects due to the number of voxels that are accommodated within the radiation field of the cone.
The measured OFs are in good agreement with data reported by Varian within 1% shown in Fig. 4. The measured and MC-simulated OFs exhibit good agreement for cone sizes 10 mm and above. However, considerable deviations were observed below 10 mm for 7·5 mm and 5 mm cones. The agreement between measured and MC OFs for the largest cone of 17·5 mm and the smallest cone of 5 mm were found 0·26 % and 4·78 %, respectively. The agreement was poorer for the smallest cone size of 5 mm diameter. The diode detectors have limitations caused by volume averaging and water nonequivalence could predominantly affect measured OFs. Therefore, OFs measured with a diode detector need to be corrected to minimize effect due to its limitations. The use of the intermediate Daisy-chain method minimized the difference between measured and MC OFs. 23 However, the response of the diode detectors may be directional and energy-dependent which could lead to dosimetric uncertainties up to ± 15% are beyond the scope of correction of our work. Reference Saini and Zhu25
Gamma analysis helps in the characterization of dosimetric data such as PDD and profile. Gamma analysis facilitates the quantitative evaluation of dose distribution presented by Low et al. Reference Low, Harms, Mutic and Purdy20 The maximum value of ϒ2%/1mm corresponding to the maximum dose difference is below 0·5 and 0·9 for PDDs and profiles of all the cones, respectively. The values of ϒ2%/1mm in all regions of PDDs or profiles are below 1. Both % DD and DTA lie below the passing criteria for PDD. However, for profile DDs are higher in the dose gradient region whereas DTA are well within the limit. This established good agreements between measured and MC PDDs or profiles for all cones except for the 5 mm cone. Figures 5 and 6 illustrate the comparison of measured and simulated PDD and lateral profile distribution with gamma index for diameter of 10 mm cone, respectively.
Comparison of measured PDD relative to MC. This also illustrates variation of gamma index along the depth of PDD and percentage of gamma passing.
Comparison of measured lateral dose profile relative to MC. This also illustrates variation of percentage dose and gamma index with position for 10 mm cone size.
Conclusion
The MC model of eclipse cone for 6 MV FFF beam from a Truebeam linac was presented in PRIMO. The study presents the MC validation of experimental beam data required for the commissioning of CDC algorithm used in eclipse TPS. An overall good agreement was found between experimentally measured and MC-simulated data. It was also found that the degree of agreement subsides, as the cone size gets smaller below 10 mm. The dosimetry dataset obtained in this study validated using MC model may be used to benchmark beam data measured for commissioning of SRS cone for the eclipse planning system.
Acknowledgements
The author would like to thank to people who drove him for their continuous assistance and encouragement and made this work possible.
Financial support
No financial support or funding provided for this study.
Competing interests
Authors declare no conflict of interest.
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