Oncology Journal of India

: 2019  |  Volume : 3  |  Issue : 2  |  Page : 28--37

Clinical dosimetric impact of AAA and Acuros XB on high-density metallic implants in case of carcinoma cervix

Manindra Bhushan1, Girigesh Yadav2, Deepak Tripathi3, Lalit Kumar4, Vimal Kishore5, Rahul Lal Chowdhary2, Gourav Kumar2, Soumya Datta2, Swarupa Mitra2, Munish Gairola2,  
1 Department of Radiation Oncology, Division of Medical Physics, Rajiv Gandhi Cancer Institute and Research Centre, New Delhi; Department of Physics, Amity School of Applied Sciences, Amity University (AUUP), Noida, Uttar Pradesh, India
2 Department of Radiation Oncology, Division of Medical Physics, Rajiv Gandhi Cancer Institute and Research Centre, New Delhi, India
3 Department of Physics, Amity School of Applied Sciences, Amity University (AUUP), Noida, Uttar Pradesh, India
4 Department of Radiation Oncology, Division of Medical Physics, Rajiv Gandhi Cancer Institute and Research Centre, New Delhi; Department of Applied Science and Humanities, Dr. APJ Abdul Kalam Technical University, Lucknow, Uttar Pradesh, India
5 Department of Applied Science and Humanities, Bundelkhand Institute of Engineering and Technology, Jhansi, Uttar Pradesh, India

Correspondence Address:
Mr. Manindra Bhushan
Department of Radiation Oncology, Division of Medical Physics, Rajiv Gandhi Cancer Institute and Research Centre, Sector-5, Rohini, New Delhi - 110 085


Background: Metallic implant in radiotherapy leads to difficulty in tumor target and critical organ delineation. Four-field box technique is conventional approach to treat pelvic malignancies. Aim of the Study: The aim of study is to evaluate the dosimetric impact of calculation algorithms in the treatment of carcinoma cervix with metallic implants. Materials and Methods: A paraffin wax-coated iron rod was used to evaluate the beam characteristics under the influence of metallic implant. Beam characteristics such as tissue phantom ratio (TPR20,10) were measured and analyzed. 15 patients with and without metallic prosthesis of carcinoma cervix were compared in the study. Planning was done for the prescription dose of 45 Gy/25 fractions. Plans were calculated using AAA algorithm and recalculated using Acuros XB (AXB) and pencil beam convolution algorithms for the same monitor units. RTOG and Quantec Protocol were used for plan evaluation. Results: Transmission and TPR20,10increases with field size and beam energy. Surface dose Dsalso increases with field size. D98%and D2%of planning target volume showed a significant difference for AAA versus AXB. 4FN (AAA) are significantly better for all the 4F plans, calculated by three algorithms in case of V15Gyof small bowel. Analyzed data indicated the significant attenuation caused by high-Z material. Analyzed value of conformity index showed that value of index comes >1 in all the cases. Conclusion: The results indicate that when creating treatment plans for cervical cancer lesions with metallic prosthesis, the AAA algorithm would be a more appropriate choice.

How to cite this article:
Bhushan M, Yadav G, Tripathi D, Kumar L, Kishore V, Chowdhary RL, Kumar G, Datta S, Mitra S, Gairola M. Clinical dosimetric impact of AAA and Acuros XB on high-density metallic implants in case of carcinoma cervix.Oncol J India 2019;3:28-37

How to cite this URL:
Bhushan M, Yadav G, Tripathi D, Kumar L, Kishore V, Chowdhary RL, Kumar G, Datta S, Mitra S, Gairola M. Clinical dosimetric impact of AAA and Acuros XB on high-density metallic implants in case of carcinoma cervix. Oncol J India [serial online] 2019 [cited 2020 Feb 24 ];3:28-37
Available from: http://www.ojionline.org/text.asp?2019/3/2/28/266978

Full Text


Hip fractures are common cause of morbidity and mortality in women of older age group. In a published Swedish study,[1] data showed that significant deaths occurred due to hip fractures in the people of the age 50 years or above.

It is known that the radiation delivered for treating the patients may lead to bone damage and further can result as fracture. Although the data related to radiation-induced fractures are scarce, it is a thing not to be ignored off.

It has been a conventional approach to use four-field box technique to treat pelvic malignancies before the evolution of intensity-modulated radiation therapy (IMRT). In IMRT, a dedicated planning system is used to optimize the beam intensities to conform the planning target volume (PTV) precisely while minimizing the dose to critical structures. IMRT has become widely accepted due to these features.[2],[3]

Metallic hip prostheses are made up of high-Z materials. Due to scattering of radiation signals in computed tomography (CT) images, these metallic hips produce streak artifacts [Figure 1]. This leads to difficulty in tumor target and critical organ delineation. In addition to this, the commercially available planning systems do not calculate accurately in the near and far regions of metallic hip implants, due to deviation from beam modeling parameters. However, in the presence of metallic hip prosthesis, the dose distribution alters due to beam attenuation and inhomogeneity.[4],[5],[6] The technique using intensity modulation may be a better alternative to treat such patients.{Figure 1}

The report of AAPM Task Group 63 reveals the fact that around 1%–4% of radiotherapy patient population is having metallic implant which is of high-Z materials.[7] Cobalt–Chromium–Molybdenum alloy is considered to be the best choice for hip prostheses due to its feature of fatigue and corrosion resistance and mechanical strength. As an alternative, prostheses made up of stainless steel and titanium is also commercially available and widely acceptable in clinics.[8],[9]

Many a time, the actual geometry of the prostheses is not known which will further overdose or underdose the target. These practical difficulties lead to compromise target treatment.[10]

Catlı and Tanir[11] published a study showing evaluation of Eclipse TPS for dose distribution of the patient having hip prostheses. They showed that the significant changes of dose occurred due to radiation scattering for high-Z material of hip prostheses. They observed that the dose difference depends on density and type of prostheses material as well as photon energy used for treatment planning. It was found that the metallic prostheses create significant dose perturbation, and pencil beam convolution (PBC) algorithm cannot predict the dose accurately.

Availability of Monte Carlo (MC) algorithm for dose calculation in such patient's treatment planning has shown a significant improvement and can be used as gold standard.[12],[13]

Ojala et al.[14] analyzed the accuracy of Acuros XB (AXB) algorithm and compared with the MC simulation for the volumetric modulated arc therapy and found a good agreement between two algorithms. Their study showed that the AXB calculated the dose in the vicinity and inside the prostheses of high-Z material accurately.

IMRT has become popular after advancement of technology for treating patients having deadly malignancies; but, generating a plan for patient having metallic implant is still a challenge. The high atomic number material not only creates streak artifacts in CT images but also significantly attenuates the laterally placed fields. Fattahi and Ostapiak[15] found that intrafraction motion error can be about 5cGy per mm for 2 Gy fraction dose for the match planes.

Radiotherapy planning for the patients having metallic implants is complicated due to few reasons. The metallic hip prostheses create severe streak artifacts that create difficulty in target and critical organ delineation. Second, the electron density near or within the prosthesis deviates significantly from the original values, resulting in dose calculation error.[16] In addition, the approximate percentage of attenuation is around 10%–64% for the beam passing through the prostheses, requires accuracy in modulation. However, the complication of target delineation can be overcome by fusing magnetic resonance imaging with CT images. However, the other two difficulties can be avoided by choosing suitable beam angles to ignore metallic prostheses in dose calculation. It has been shown that the dose to a point, distal to prosthesis, for a single megavoltage photon beam attenuates significantly and reduction in dose appears as 10%–40% as compared to homogeneous medium.[17]

It has been found by many researchers that the dose calculation algorithms such as PBC, Collapsed Cone (CC), and AAA behave differently in the presence of complex geometry with inhomogeneity along the beam path.[18],[19],[20],[21],[22] In fact, the dose calculation algorithms, i.e., AAA and CC are basically the convolution/superposition algorithms which takes care the primary and secondary dose kernel, derived by MC simulation.[23]

AAA is considered superior as it considers the dose inhomogeneity correction in beam direction (the direction of dose deposition) as well as in the lateral direction, including the electron density-based photon scatter of beam.[24],[25] Liu et al. compared the dosimetric parameters of treatment plans of carcinoma lung patients, calculated by AAA and AXB calculation algorithms. They found that the AXB achieves low conformity and higher heterogeneity for the target when compared to AAA.[26]

Kroon et al. evaluated the plans of lung cancer patients of Stage I and Stage III and found that the PTV doses differ around −12.3% and −0.8% in respective stages with the dose calculated by AXB, as compared to AAA.[27] The PTV mean dose was lower by −4.9% when calculated by AXB and was compared with AAA plans.

Rana et al. also published that the mean doses and maximum doses to PTV were lowered by −0.3% and −4.3%, respectively, when calculated by AXB algorithm.[28] Khan et al. found that the monitor units (MUs) required delivering the same prescribed dose were 2% higher for AXB calculated plans when compared with AAA calculated plans.[29]

The aim of the study is to evaluate the dosimetric impact of calculation algorithms in the presence of metallic hip implants in the treatment of carcinoma cervix.

 Materials and Methods

Phantom metal implant

Phantom preparation

Density of steel and iron are approximately similar (d = 7.87 g/cm3 and d = 7.81 g/cm3 respectively). Since stainless steel is used as clinical prosthesis, we used iron metal to fabricate the similar implant. To evaluate the beam characteristics under the influence of metallic implant, an indigenously made phantom was used. The cylindrical phantom was made using iron rod and covered with paraffin wax coating. Paraffin wax was used to simulate the effect of adjacent tissues. The dimension of the phantom is shown in [Figure 2].{Figure 2}


The measurements were carried out on Varian Clinac-iX Linear Accelerator (Varian Medical Systems, Palo Alto, CA, USA) using phantom metal implant (PMI). PMI was placed on a Perspex tray in the central axis of the 6MV beam at the minimum possible distance from the X-ray source. The beam profiles were taken for three field size, i.e., 5 cm × 5 cm, 10 cm × 10 cm, and 20 cm × 20 cm for two depths as dmax(1.5 cm) and 10 cm. Percentage depth dose was also measured for above field sizes. All the measured profiles and dose curve were compared with normal 6MV and 15MV beam, and data were tabulated. Experimental setup is shown in [Figure 3].{Figure 3}

Tissue Phantom Ratio20,10

Measurements were performed using CC13 chamber (IBA Dosimetry, Germany) having active volume 0.13 cc. Chamber was placed inside a 30 cm × 30 cm × 30 cm water phantom at the two different depths, i.e., 20 cm and 10 cm, keeping source-to-axis distance at 100 cm. Chamber was exposed for 100 MUs, and the ratio was established for the charge collected, for the above respective depths. Data were gathered for with and without PMI as shown in [Figure 4] and [Figure 5] for 6MV and 15MV, respectively.{Figure 4}{Figure 5}

Surface dose (Ds)

Parallel plate chamber 40 (IBA Dosimetry, Germany) was used to measure the surface doses. Chamber was kept at the surface with source-to-surface distance (SSD) as 100 cm along with a water phantom (dimension 30 cm × 30 cm × 30 cm). Charge was collected for different field sizes when exposed for 100 MUs, with and without PMI and shown in [Figure 6].{Figure 6}

Percentage depth dose

The measurements were carried out using CC13 thimble chamber (IBA Dosimetry, Germany), by placing at the central axis with SSD at 100 cm, inside a Radiation Field Analyzer, Blue Phantom (IBA Dosimetry, Germany). The data were captured up to the depth of 31 cm inside the water. Measurements were done for small field size 5 cm × 5 cm, reference field size 10 cm × 10 cm, and large field size 20 cm × 20 cm for with and without PMI. Software OmniPro Accept v7.0 (IBA Dosimetry, Germany) was used for analysis [Table 1].{Table 1}


In-air measurements were carried out to measure the attenuation, caused by metallic implant. Farmer chamber FC-65 (IBA Dosimetry, Germany) with a buildup cap was used to assess the effect of transmission through PMI. Chamber was kept in air at source-to-detector distance 100 cm and exposed for 100 MUs for different field sizes. Measurements were performed for with and without PMI, and ratio was established to get the transmission factor [Figure 7] and [Figure 8].{Figure 7}{Figure 8}

Beam profile

Beam profiles were measured using Radiation Field Analyzer, Blue Phantom (IBA Dosimetry, Germany). CC13 thimble chamber (IBA Dosimetry, Germany) and IC15 ion chamber (IBA Dosimetry, Germany) were used for relative dosimetry by placing the CC13 at SSD at 100 cm. Inline and crossline profiles were taken for small field size 5 cm × 5 cm, reference field size 10 cm × 10 cm, and large field size 20 cm × 20 cm for with and without PMI. OmniPro Accept v7.0 (IBA Dosimetry, Germany) Software was used for analysis [Figure 9] and [Table 2].{Figure 9}{Table 2}

Clinical evaluation

Patient selection and simulation

15 patients of carcinoma cervix having metallic hip implant were included in the study and compared with similar another 15 patients without hip prosthesis of cervical cancer. Before 30 min of CT scan, the patient was asked to drink water to fulfill the bladder protocol. The patient was immobilized using Orfit Cast and AIO. CT scan was taken in the supine position. In-room lasers were used to align the patient, and the position was verified by using a topograph. The slices acquired were of 3 mm thickness, and the acquired CT data series was sent to TPS using digital communication. The target volumes and critical structures were contoured by oncologist as per guidelines of RTOG, and the planning was done by medical physicist.


PTV and nearby critical structures were drawn for all the patients on their respective tomographic images using SomaVision workstation (Varian Medical System, Palo Alto, California, USA). Clinical target volume (CTV) included lymphonodal region, uterus, adnexa, and vagina. Lymphonodal region included common iliac, external iliac, internal iliac, presacral, and obturator. PTV was generated by giving 5.0 mm margin to CTV. Critical structures such as bladder, rectum, femoral heads, and bowel loop were also delineated. RTOG guidelines were followed in delineating the contours.[30],[31]

Treatment planning

The planning was done for the prescription dose of 45 Gy/25 fractions as 1.8 Gy per fraction for all the patients. For each patient, the planner has made fix isocentric plans with the same isocenter in the present study. Varian Clinac-iX linear accelerator (Varian Medical System, Palo Alto, California, USA), equipped with millennium-multileaf collimator (m-MLC) was used for the treatment delivery. M-MLC is characterized by special resolution of 40 mm × 5.0 mm central leaves and 20 mm × 10.0 mm in outer leaves.

Conventional approach of treating the target by 4-field box technique has an advantage that it reduces the chances of tumor missing in the field border areas.

Plans were made using gantry angles 0, 180, 90, and 270 with collimator 0 and couch 0. Plans were calculated using AAA algorithm and recalculated using AXB and PBC algorithms for the same MUs as obtained in AAA calculated plans.

This exercise was done to evaluate the effect of different algorithms on the dose calculations irrespective of MUs.

Evaluation parameters

The protocol given by Quantec et al. was used to evaluate the doses to PTV and critical structures. Using cumulative dose-volume-histogram, the following parameters were evaluated:

PTV: D98%, D95%, D50%, D2%, D107%, D110%, conformity index (CI98%), homogeneity index (HI)Bladder: D50Gy, Dmax, Dmean, D2ccRectum: D50Gy, Dmax, Dmean, D2ccBowel: D5 Gy, D30 Gy, Dmean, V15 Gy, V45 GyLeft femoral head: D50 Gy, DmeanRight Femoral Head: D50 Gy, Dmean.

Here, Dx% denotes the dose received by “x”% of the target volume and DyGy denotes the percentage volume of the organ receiving “y”Gy dose. D2cc is the dose received by 2cc volume of the organ. However, VzGy is the absolute volume of the structure covered by “z”Gy dose. Dmax and Dmean are the maximum and mean dose of the structure, respectively.

Conformity index

The CI corresponds to the dose coverage. CI equal to 1 is an ideal condition, and in case, CI > 1 indicates that irradiated volume exceeds the target volume and covers part of the healthy tissues. It may be defined as:[32],[33],[34],[35]

CI98= Volume of 98% isodose/PTV volume

The value of CI less than one indicates partial irradiation of the target volume. It is difficult to achieve the ideal value; RTOG define a range of CI values to judge the quality of conformity, as discussed below:

CI: Between 1.0 and 2.0, the treatment is well with the protocolCI: Between 2.0–2.5 and 0.9–1.0, minor deviation from the protocolCI > 2.5 and <0.9, severe deviation from the protocol.

Homogeneity index

Dose index (HI) is an objective tool to analyze the uniformity of dose distribution in the target volume. It may be defined as:[36],[37]

HI = (D2%− D98%)/D50%

HI98= D2%/D98

Statistical analysis

Data were analyzed using paired-t test using SPSS software 20.0 (SPSS Inc., Chicago, IL, USA). P < 0.05 was considered as statistically significant.


For phantom metal implant

Few most significant parameters related to beam characteristics were evaluated. Transmission through the prosthesis material increases with field size, irrespective of beam energy. Tissue phantom ratio (TPR20,10) is important parameter related to beam quality. TPR20,10 increases with field size and beam energy. Surface dose Ds also increases with field size.

For clinical cases

Four-field plan (4F) was made for patients having hip prosthesis, and another 4-field plan (4FN) was related to the patients without hip prosthesis. D98% of PTV was 48.41 (SD: 1.004), 48.07 (SD: 1.005), 52.69 (SD: 1.099), 49.01 (SD: 0.852), 48.54 (SD: 0.796), and 53.37 (SD: 0.721) Gy for 4FN (AAA), 4FN (AXB), 4FN (PBC), 4F (AAA), 4F (AXB), and 4F (PBC), respectively. Analysis showed a significant difference for AAA and AXB (P = 0.001 and P = 0.009) for both the techniques [Table 3].{Table 3}

Similarly, to evaluate the maximum dose to PTV, D2% were 55.44 (SD: 1.77), 55.29 (SD: 1.76), 59.88 (SD: 1.93), 56.59 (SD: 1.71), 56.23 (SD: 1.82), and 60.89 (SD: 1.84) Gy for 4FN (AAA), 4FN (AXB), 4FN (PBC), 4F (AAA), 4F (AXB), and 4F (PBC), respectively. Data showed a significant difference in D2% for AAA versus AXB (P = 0.003) for 4FN as well as for AAA versus PBC (P = 0.001) for 4F treatment plans [Figure 10].{Figure 10}

Percentage volume of bladder receiving 50 Gy (D50Gy) were 80.16 (SD: 12.51), 74.56 (SD: 16.56), 87.07 (SD: 10.65), 93.81 (SD: 6.78), 92.81 (SD: 7.53), and 96.54 (SD: 3.75) % for 4FN (AAA), 4FN (AXB), 4FN (PBC), 4F (AAA), 4F (AXB), and 4F (PBC), respectively. The data showed a significant difference of AAA for 4FN versus 4F plans (P = 0.022). Similarly, the data indicate a significant difference for AAA and PBC in 4FN treatment technique (P = 0.018).

The maximum dose to rectum were 51.57 (SD: 0.92), 51.61 (SD: 1.02), 55.95 (SD: 1.09), 53.13 (SD: 1.88), 52.99 (SD: 1.66), and 57.43 (SD: 1.58) Gy for 4FN (AAA), 4FN (AXB), 4FN (PBC), 4F (AAA), 4F (AXB), and 4F (PBC), respectively. Analysis showed that the 4FN (AAA) has edge over 4F (AXB) with significant difference in the values (P = 0.031). However, there is significant difference between AXB and PBC calculation for 4FN plans (P = 0.001).

The mean doses to bowel were 23.88 (SD: 5.72), 23.71 (SD: 5.69), 25.43 (SD: 6.27), 24.67 (SD: 5.65), 24.28 (SD: 5.53), and 26.37 (SD: 5.98) for 4FN (AAA), 4FN (AXB), 4FN (PBC), 4F (AAA), 4F (AXB), and 4F (PBC), respectively. The data showed that the AXB has an edge over AAA calculated 4F plans (P = 0.015). However, 4FN (AAA) are significantly better for all the 4F plans, calculated by three algorithms (P = 0.005, P = 0.005 and P = 0.004) in case of V15Gy[Figure 11].{Figure 11}


Analyzed data indicated the significant attenuation caused by high-Z material. Increased transmission with field size and beam energy may be due to added contribution of scatter beam component into the primary dose. It is clear that prosthetic implant dramatically increases the value of TPR20,10, i.e., beam quality. This increases the average energy of beam, and finally, the whole dose distribution got affected. Variation of surface dose is due to implanted material as the prosthesis attenuates the beam significantly.

The use of prosthesis and implants are rapidly increasing in the form of variety of materials like plastic, metals, and ceramics. These materials present in the vicinity of tissues affect the dose delivered by radiotherapy. It is important to assess the effect of these devices on treatment plan, especially when the accurate dimension and description of the implant is not known. Of all these materials, metals are the matter of most concern.

Any perturbation to the implant will depend on composition of the prosthesis and the beam characteristics like beam energy. Having hip prosthesis in the radiotherapy planning for the treatment of pelvic tumors has always been a difficult task due to the dose alteration by the metallic prosthesis.

Hudson et al. demonstrated that the shadowing by the prosthesis may be an important factor for dose difference in radiotherapy plan.[38] Biggs and Russell described that a hollow prosthesis with 5 cm diameter and 3 mm wallthickness may underdose the target by 2% for 25 MV X-rays and overdose the tumor by 2% for 10MV X-rays and 5% for Co-60 beam.[39] Sibata et al. found that the algorithm used in the planning may be used to predict the dose distribution under a femoral hip prosthesis within acceptable uncertainty.[40] It was also found that up to 50% attenuation may occur for a solid implant.

In this study, we compared the dosimetric quality of 4-field plans for cervical cancer patients with metallic hip prosthesis, and the dosimetric evaluation was done by applying equal MUs for all the calculation algorithms. In this study, we demonstrated the dosimetric quality of box technique using four fields to treat the patients of carcinoma cervix with a single metallic hip prosthesis.

Analyzed value of CI showed that value of index comes >1 in all the cases. Even though it is within the tolerance protocol, higher value indicates obvious radiation of healthy tissues due to box technique [Figure 12].{Figure 12}

Fragoso et al. also observed a marked reduction in calculated dose to the PTV when PBC-based plans were re-calculated with the MC-based algorithm. The minimum PTV doses shown with the PBC and MC were 97% and 58%, respectively. The 80% and 95% isodose lines covering the intermediate target volume and PTV shown in a lung patient study, when calculated with PBC, did not encompass the PTV when recalculated with MC.[41] A similar trend was also found in our study.

D50 as well as mean dose to the bladder and rectum are significantly lower for the patients without hip prosthesis, calculated by AAA and AXB. Lloyd and Ansbacher also concluded that AXB algorithm is a beneficial dose calculation tool for treatments with high-Z materials, as its accuracy is equal to MC, yet fast enough for clinical application.[42]

Mean dose to bowel were significantly better for AXB calculated plans when compared with AAA and PBC. Erlanson M et al. also demonstrated that there were small deviations in dose distributions calculated by the AXB algorithm, on average within 2.5%, when compared to the MC model.[17] Oinam and Singh found that for the surface areas of 1, 50, and 100 cm2, PBC overestimates doses as compared to AAA calculated value in the range of 1.34%–3.62% at 0.6 cm depth. In high-dose buildup region, AAA calculated doses were lower by an average of − 7.56% (SD: 4.73%), while PBC was overestimated by 3.75% (SD: 5.7%). They concluded that AAA calculated the dose more accurately than PBC in clinically important depths.[43] Furthermore, AAA is considered more appropriate in our study due to the findings such as dose coverage of PTV and lesser dose to critical structures as well as on the basis of related studies given in the references.


The results from this study indicate that when creating treatment plans for cervical cancer lesions with metallic prosthesis, the AAA algorithm, a scatter-based dose model with increased accuracy in scattered dose calculation, would be a more appropriate choice. If one decides to use the AAA calculation algorithm, the prescribed dose should be adjusted down by 10%–14% to maintain equivalence to plans generated by the PBC algorithm.

Financial support and sponsorship


Conflicts of interest

There are no conflicts of interest.


1Kanis JA, Oden A, Johnell O, De Laet C, Jonsson B, Oglesby AK. The components of excess mortality after hip fracture. Bone 2003;32:468-73.
2Tyagi A, Supe SS, Sandeep, Singh MP. A dosimetric analysis of 6 MV versus 15 MV photon energy plans for intensity modulated radiation therapy (IMRT) of carcinoma of cervix. Rep Pract Oncol Radiother 2010;15:125-31.
3Simson DK, Mitra S, Ahlawat P, Sharma MK, Yadav G, Mishra MB, et al. Dosimetric comparison between intensity modulated radiotherapy and 3 dimensional conformal radiotherapy in the treatment of rectal cancer Asian Pac J Cancer Prev 2016;17:4935-7.
4Su A, Reft C, Rash C, Price J, Jani AB. A case study of radiotherapy planning for a bilateral metal hip prosthesis prostate cancer patient. Med Dosim 2005;30:169-75.
5Hazuka MB, Ibbott GS, Kinzie JJ. Hip prostheses during pelvic irradiation: Effects and corrections. Int J Radiat Oncol Biol Phys 1988;14:1311-7.
6Grigsby PW, Roberts HL, Perez CA. Femoral neck fracture following groin irradiation. Int J Radiat Oncol Biol Phys 1995;32:63-7.
7Reft C, Alecu R, Das IJ, Gerbi BJ, Keall P, Lief E, et al. Dosimetric considerations for patients with HIP prostheses undergoing pelvic irradiation. Report of the AAPM Radiation Therapy Committee Task Group 63. Med Phys 2003;30:1162-82.
8Keall PJ, Siebers JV, Jeraj R, Mohan R. Radiotherapy dose calculations in the presence of hip prostheses. Med Dosim 2003;28:107-12.
9Tatcher M, Palti S. Evaluation of density correction algorithms for photon-beam dose calculations. Radiology 1981;141:201-5.
10Alves GG, Kinoshita A, Oliveira HF, Guimarães FS, Amaral LL, Baffa O. Accuracy of dose planning for prostate radiotherapy in the presence of metallic implants evaluated by electron spin resonance dosimetry. Braz J Med Biol Res 2015;48:644-9.
11Catlı S, Tanır G. Experimental and Monte Carlo evaluation of eclipse treatment planning system for effects on dose distribution of the hip prostheses. Med Dosim 2013;38:332-6.
12Farajollahi A, Mesbahi A. Monte Carlo dose calculations for a 6-MV photon beam in a thorax phantom. Radiat Med 2006;24:269-76.
13Mesbahi A, Thwaites DI, Reilly AJ. Experimental and Monte Carlo evaluation of eclipse treatment planning system for lung dose calculations. Rep Pract Oncol Radiother 2006;11:123-33.
14Ojala J, Kapanen M, Sipilä P, Hyödynmaa S, Pitkänen M. The accuracy of acuros XB algorithm for radiation beams traversing a metallic hip implant – Comparison with measurements and Monte Carlo calculations. J Appl Clin Med Phys 2014;15:4912.
15Fattahi S, Ostapiak OZ. An opposed matched field IMRT technique for prostate cancer patients with bilateral prosthetic hips. J Appl Clin Med Phys 2012;13:3347.
16Schreiner LJ, Rogers M, Salamons G, Kerr A. Metal artifact suppression in megavoltage computed tomography. In: Flynn MJ, editor. Medical Imaging 2005: Physics of Medical Imaging. Proceedings of SPIE. Vol. 5745. Bellingham, WA: SPIE; 2005.
17Erlanson M, Franzén L, Henriksson R, Littbrand B, Löfroth PO. Planning of radiotherapy for patients with hip prosthesis. Int J Radiat Oncol Biol Phys 1991;20:1093-8.
18Gray A, Oliver LD, Johnston PN. The accuracy of the pencil beam convolution and anisotropic analytical algorithms in predicting the dose effects due to attenuation from immobilization devices and large air gaps. Med Phys 2009;36:3181-91.
19Kan MW, Cheung JY, Leung LH, Lau BM, Yu PK. The accuracy of dose calculations by anisotropic analytical algorithms for stereotactic radiotherapy in nasopharyngeal carcinoma. Phys Med Biol 2011;56:397-413.
20Fogliata A, Vanetti E, Albers D, Brink C, Clivio A, Knöös T, et al. On the dosimetric behaviour of photon dose calculation algorithms in the presence of simple geometric heterogeneities: Comparison with Monte Carlo calculations. Phys Med Biol 2007;52:1363-85.
21Robinson D. Inhomogeneity correction and the analytic anisotropic algorithm. J Appl Clin Med Phys 2008;9:2786.
22Gagné IM, Zavgorodni S. Evaluation of the analytical anisotropic algorithm in an extreme water-lung interface phantom using Monte Carlo dose calculations. J Appl Clin Med Phys 2006;8:33-46.
23Sievinen J, Ulmer W, Kaissl W. AAA Photon dose Calculation Model in Eclipse. Palo Alto, CA: Varian Medical Systems; 2005.
24Ulmer W, Pyyry J, Kaissl W. A 3D photon superposition/convolution algorithm and its foundation on results of Monte Carlo calculations. Phys Med Biol 2005;50:1767-90.
25Tillikainen L, Helminen H, Torsti T, Siljamäki S, Alakuijala J, Pyyry J, et al. A3D pencil-beam-based superposition algorithm for photon dose calculation in heterogeneous media. Phys Med Biol 2008;53:3821-39.
26Liu HW, Nugent Z, Clayton R, Dunscombe P, Lau H, Khan R. Clinical impact of using the deterministic patient dose calculation algorithm acuros XB for lung stereotactic body radiation therapy. Acta Oncol 2014;53:324-9.
27Kroon PS, Hol S, Essers M. Dosimetric accuracy and clinical quality of acuros XB and AAA dose calculation algorithm for stereotactic and conventional lung volumetric modulated arc therapy plans. Radiat Oncol 2013;8:149.
28Rana S, Rogers K, Lee T, Reed D, Biggs C. Verification and dosimetric impact of Acuros XB algorithm for stereotactic body radiation therapy (SBRT) and RapidArc planning for non-small-cell lung cancer (NSCLC) patients. Int J Med Phys Clin Eng Radiat Oncol 2013;2:6-14.
29Khan RF, Villarreal-Barajas E, Lau H, Liu HW. Effect of acuros XB algorithm on monitor units for stereotactic body radiotherapy planning of lung cancer. Med Dosim 2014;39:83-7.
30Small W Jr., Mell LK, Anderson P, Creutzberg C, De Los Santos J, Gaffney D, et al. Consensus guidelines for delineation of clinical target volume for intensity-modulated pelvic radiotherapy in postoperative treatment of endometrial and cervical cancer. Int J Radiat Oncol Biol Phys 2008;71:428-34.
31Yadav G, Bhushan M, Dewan A, Saxena U, Kumar L, Chauhan D, et al. Dosimetric influence of photon beam energy and number of arcs on volumetric modulated arc therapy in carcinoma cervix: A planning study. Rep Pract Oncol Radiother 2017;22:1-9.
32Kumar L, Yadav G, Samuvel KR, Bhushan M, Kumar P, Suhail M, et al. Dosimetric influence of filtered and flattening filter free photon beam on rapid arc (RA) radiotherapy planning in case of cervix carcinoma. Rep Pract Oncol Radiother 2017;22:10-8.
33Feuvret L, Noël G, Mazeron JJ, Bey P. Conformity index: A review. Int J Radiat Oncol Biol Phys 2006;64:333-42.
34Petrova D, Smickovska S, Lazarevska E. Conformity index and homogeneity index of the postoperative whole breast radiotherapy. Open Access Maced J Med Sci 2017;5:736-9.
35Richmond ND, Turner RN, Dawes PJ, Lambert GD, Lawrence GP. Evaluation of the dosimetric consequences of adding a single asymmetric or MLC shaped field to a tangential breast radiotherapy technique. Radiother Oncol 2003;67:165-70.
36ICRU Report 83, Journal of the ICRU. Vol. 10. Oxford University Press; 2010.
37Sharma MK, Hug EB, Bhushan M, Mah D, Maes D, Gairola M, et al. Dosimetric comparison of pencil-beam scanning and photon-based radiation therapy as a boost in carcinoma of cervix. Int J Part Ther 2017;4:1-10. [DOI: 10.14338/IJPT-17-00009].
38Hudson FR, Crawley MT, Samarasekera M. Radiotherapy treatment planning for patients fitted with prostheses. Br J Radiol 1984;57:603-8.
39Biggs PJ, Russell MD. Effect of a femoral head prosthesis on megavoltage beam radiotherapy. Int J Radiat Oncol Biol Phys 1988;14:581-6.
40Sibata CH, Mota HC, Higgins PD, Gaisser D, Saxton JP, Shin KH, et al. Influence of hip prostheses on high energy photon dose distributions. Int J Radiat Oncol Biol Phys 1990;18:455-61.
41Fragoso M, Wen N, Kumar S, Liu D, Ryu S, Movsas B, et al. Dosimetric verification and clinical evaluation of a new commercially available Monte Carlo-based dose algorithm for application in stereotactic body radiation therapy (SBRT) treatment planning. Phys Med Biol 2010;55:4445-64.
42Lloyd SA, Ansbacher W. Evaluation of an analytic linear Boltzmann transport equation solver for high-density inhomogeneities. Med Phys 2013;40:011707.
43Oinam AS, Singh L. Verification of IMRT dose calculations using AAA and PBC algorithms in dose buildup regions. J Appl Clin Med Phys 2010;11:3351.