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Int J Med Sci 2011; 8(6):461-466. doi:10.7150/ijms.8.461

Research Paper

Patient Specification Quality Assurance for Glioblastoma Multiforme Brain Tumors Treated with Intensity Modulated Radiation Therapy

H. I. Al-Mohammed Corresponding address

King Faisal Specialist Hospital & Research Centre, Dept. of Biomedical Physics, Riyadh 11211, Saudi Arabia

This is an open access article distributed under the terms of the Creative Commons Attribution (CC BY-NC) License. See http://ivyspring.com/terms for full terms and conditions.
How to cite this article:
Al-Mohammed HI. Patient Specification Quality Assurance for Glioblastoma Multiforme Brain Tumors Treated with Intensity Modulated Radiation Therapy. Int J Med Sci 2011; 8(6):461-466. doi:10.7150/ijms.8.461. Available from http://www.medsci.org/v08p0461.htm

Abstract

The aim of this study was to evaluate the significance of performing patient specification quality assurance for patients diagnosed with glioblastoma multiforme treated with intensity modulated radiation therapy. The study evaluated ten intensity modulated radiation therapy treatment plans using 10 MV beams, a total dose of 60 Gy (2 Gy/fraction, five fractions a week for a total of six weeks treatment). For the quality assurance protocol we used a two-dimensional ionization-chamber array (2D-ARRAY). The results showed a very good agreement between the measured dose and the pretreatment planned dose. All the plans passed >95% gamma criterion with pixels within 5% dose difference and 3 mm distance to agreement. We concluded that using the 2D-ARRAY ion chamber for intensity modulated radiation therapy is an important step for intensity modulated radiation therapy treatment plans, and this study has shown that our treatment planning for intensity modulated radiation therapy is accurately done.

Keywords: Photon-beam dose calculation, quality assurance, intensity modulated radiation therapy, dose verification, gamma index, glioblastoma multiforme.

Introduction

Glioblastoma multiforme (GBM) is the most common malignant tumor of the subcortical white matter of the cerebral hemisphere in adults. It accounts for 12%-15% of all primary brain tumors [1]. The treatment of GBM involves surgical resection, which is the first therapeutic modality for GBM, followed by radiotherapy that may be accompanied by adjuvant chemotherapy [2]. In general, patients with GBM have poor prognosis with about 20% of patients surviving beyond 2 years [2]. However, some factors may be associated with a longer survival rate. These factors include younger age, gender, unilateral tumor, a high Karnofsky score, size of the tumor, extent of disease, and adjuvant treatments with chemotherapy such as temozolomide (TMZ) [3].

In recent years, the development of state-of-the-art radiation therapy and recent advances in chemotherapy have increased the chances for a good prognosis for GBM patients [4]. Intensity modulated radiotherapy (IMRT) allows for a high dose of radiation to be delivered to the tumor while permitting maximal sparing of normal tissue which reduces the radiation toxicity [5-9]. In the case of glioblastoma multiforme, IMRT has shown the potential to deliver a highly conformal dose to the target while minimizing dose to the organs at risk (OAR) such as the optic chiasm [10]. This can allow for dose escalation, while on the other hand, also increase local control [6, 7,11]. Treatment with IMRT fields involves the complex movement of a multileaf collimator (MLC) which consists of many small and irregular multileaf fields or segments that can be delivered in two main modalities, namely segmental IMRT step-and-shoot (SS) or dynamic IMRT (sliding window) [12]. In the IMRT step-and-shoot (SS) technique, the shape of the leaves stays constant while the radiation beam is on and changes when the radiation beam is off, while in the dynamic sliding window technique each leaf pair moves continuously in one direction with independent speeds while the radiation beam is on [13].

IMRT dose distributions have the characteristics of complex 3-dimensional dose gradients and a time- dependent fluence delivery [14]. These complex characterizations make quality assurance for every IMRT treatment compulsory. The goals of the pretreatment quality assurance are to assure the precision of the IMRT treatment plan and the application of the prescribed dose from the plan [13]. As a consequence of the complexity of the IMRT technique, additional dose checking methods are required to confirm the exact calculation of the dose for all patients treated with IMRT [15, 16]. The most common applied dose evaluation tools encompass a direct comparison of dose differences that have a comparison of distance-to-agreement (DTA) between the measured dose and the calculated dose distributions from the planning system [16, 17].

The checking procedure for IMRT includes several steps which then lead to the quality assurance (QA) for the whole IMRT treatment plan. These steps include the multileaf collimator (MLC) QA, the measurements of individual patient fluence maps, the calibration of the tools used, and the reproducibility of patient positioning [18]. The planned dose fluence is compared with deliverable dose fluence, usually by using a two-dimensional array with ionization chambers, electronic portal imaging devices (EPID), or radiochromic film named “Gafchromic EBT film” [19, 20]. In this study we used a two-dimensional array with 729 ionization chambers, which is a portal dose device for IMRT plan verification.

Materials and Methods

Our IMRT pretreatment dose verification method consisted of the following two independent measurements: first, point dose measurements at the isocenter using a two-dimensional detector matrix with 729 ionization chambers (2D-ARRAY) (PTW, Freiburg, Germany); and second, using RadCalc (RadCalc, Lifeline Software, Inc., Tyler, TX) to check independent monitor units (MU) for each beam. Pretreatment IMRT plans for ten patients diagnosed with GBM brain tumors were selected. For each of the ten pretreatment plans, verification IMRT plans were created using a Varian Eclipse external beam treatment planning system (Eclipse TPS) (8.1.18, Varian Medical Systems Inc., Palo Alto, CA). All IMRT verification plans have the same dosimetric parameters of the original plans. The dose was calculated using the Pencil Beam Convolution (PBC) algorithm built-in in the 3-dimensional treatment planning system. The verification plan for each patient was created to start the verification process. All treatment parameters, i.e., monitor units, field sizes, gantry angles, and leaf motion instructions, are stored in the database of ARIA Oncology (Varian Medical Systems Inc., Palo Alto, CA), which is an oncology-specific electronic medical record (EMR) that manages clinical activities such as radiation treatment.

The system is connected through a network to all of the treatment units. The two-dimensional array used in this investigation (2D-ARRAY) is equipped with 729 vented plane parallel ion chambers. Each detector covers an area of 5 x 5 mm2 and the measuring depth is at 5 mm water. The sensitive volume of each chamber is 0.125 cm3. These ionization chambers are uniformly arranged in a 27 × 27 matrix with an active area of 27 × 27 cm2 and dimensional area of 22 mm x 300 mm x 420 mm, interface: 80 mm x 250 mm x 300 mm, allowing absolute dose and dose rate measurements of high-energy photon beams.

The 2D-ARRAY chamber is calibrated using a setup of 10 cm x10 cm field size, 100 MU, 10 MV beams at a depth of 10 cm, and a dose rate of 300 cGy/MU. In favor of the verification plans, the 2D-ARRAY setup consists of three solid water slabs of polymethyl methacrylate (PMMA) with deferent thicknesses of 3 cm, 4 cm and 1 cm.

The 3 cm thickness slab was used as a backscatter phantom, where the other two slabs with a total thickness of 10 cm was used as a buildup phantom. The 2D-ARRAYchamber center was aligned with the isocenter of the plan. The 2D planar dose distribution was calculated at a 10 cm depth in the phantom using 1 mm pixel-dose grid resolution, and the point dose was calculated at the isocenter; whereas the reference point was 5 mm behind surface. The individual fields are radiated in gantry and collimator position of 0° on the array and source-to-surface distance (SSD) of 94.5 cm, using dynamic multileaf collimation on a Varian linear accelerator Clinac 2100EX equipped with the 120-leaf Millennium MLC (Varian Medical Systems Inc., Palo Alto, CA). The MLC system has 60 pairs of leaves in each bank and MLC leaf width projected at isocenter is 1 cm. The leaf ends are rounded. The 2D-ARRAY chamber is connected to a laptop outside the treatment room which runs software from PTW.

The software is MatrixScan (PTW-Verisoft 3.1) which records the measurements with the 2D-ARRAY. Prior to the treatment the temperature, pressure, and a correction factor for the machine is entered into the MatrixScan software. Each beam of the treatment plan is delivered to the 2D-ARRAY chamber, thus the dose at some reference points can be calculated. The measured dose distributions were then compared to those calculated by the Eclipse TPS. The IMRT treatment plans for each of the ten patients consisted of 5 to 11 beams using 10 MV beams with total dose of 60 Gy and a dose of 2.0 Gy. Every field is irradiated in each plan one after another on the 2D-ARRAY without interruptions or entering the treatment room and the combined dose is measured, reflecting the contribution from all beams for every plan. The measured dose by 2D-ARRAY was compared with the planned dose using verification software based on the gamma index criterion [19,20]. Comparisons between measured and calculated dose distributions are reported as dose difference (DD) (pixels within 5%), distance to agreement (DTA) (3 mm), as well as gamma values (γ) (dose 3%, distance 3 mm).

Statistical analysis

Data from each sample were run in duplicate and expressed as means ± SD (cGy, n = 10 patients). Means were considered significantly different if P < 0.05. Statistical analysis was performed by means of a GraphPad Prism™ package for personal computers (GraphPad Software, Inc., San Diego, USA) and figures were drawn using the GraFitTM package for personal computers (Erithacus Software Limited, Surrey, UK). An ANOVA analysis using Tukey's test for multiple comparison tests was performed on the data.

Results

In this study we evaluated our QA system for IMRT plans that are going to be used to treat patients with GBM brain tumors. Presently, we perform routine QA measurements for each IMRT patient either immediately prior to the treatment or shortly after the first treatment. Table 1 shows the total number of IMRT fields for the ten selected treatment plans measured, the fractional dose for each plan, and the fractional measured dose by 2D-ARRAY. Table 1 also shows the percentage dose different between the TPS and the VeriSoft software measured dose in addition to the percentage of pixels passing gamma criterion. The overall study result is shown in Figure 1. The average dose difference between planned and measured dose was -0.28% with a standard deviation of 1.06. Considering that the passing criteria for IMRT plans is based on the percentage of pixels passing gamma index >95% within dose difference (pixels is within 5%), and distance to agreement dose is 3 mm, all of our ten selected treatment plans passed the gamma analysis test with an average of 97% pixels with an SD of 0.015.

 Figure 1 

This graph shows the mean ± SD for the 10 patients of the prescribed dose and measured doses using the 2D-ARRAY ion chamber. There was no significant difference (ns) between the target fraction planned dose using TPS with either 2D-ARRAY or the dose that been calculated using RadCal. (ANOVA analysis, Tukey's test for multiple comparison tests).

Int J Med Sci Image (Click on the image to enlarge.)
 Table 1 

This data shows the fractional dose for the planned and measured radiation treatment, the RadCalc calculations, the % dose difference between TPS and VeriSoft software measured dose, and the % of pixels passing gamma criterion for the 10 patient treatment plans

Patient's fields numbersFraction Planned Dose, cGy2D-ARRAY Measured dose, cGy% dose difference between TPS and VeriSoft software measured dose% of pixels passing gamma criterion
5200.0199.80-0.10 %99%
8219.2219.850.29%97%
11219.2218.90-0.27%96%
9200.0200.700.35%97%
8219.2218.50-0.31%97%
11200.0200.000.00%100%
11200.0199.80-0.10%99%
8200.0198.90-0.55%97%
5200.0199.20-0.40%97%
7200.0200.500.25%95%
IMRT fields total of = 83Average Dose=205.73 cGyAverage Dose =205.615 cGySD= 0.00307SD=0.0151

Discussion

Glioblastoma multiforme (GBM) is the most frequently encountered and most malignant form of brain tumor, with a poor prognosis and low life expectancy [21] Intensity modulated radiation therapy (IMRT) is a new development of conformal radiotherapy which shows a better outcome for treatment, with a better sparing of the normal brain tissue and other critical structures [19]. IMRT treatment plans are complex radiotherapy treatment plans that require a comprehensive QA field-by-field in addition to complex analysis methods [20, 22]. The need for the sophisticated treatment plans and measurements increases if the tumor is located in an area surrounded by healthy and critical tissues. For example, a tumor in brain is surrounded by many organs at risk (OAR) such as the brain stem and the optic chiasm [10]. In our study we evaluated our QA system of IMRT plans that we use to treat patients with GBM.

Presently, we perform routine QA measurements for each IMRT patient either immediately prior to the treatment or shortly after the first treatment, which is the protocol we use to avoid any delay for the treatment. The ten selected treatment plans were evaluated using 2D-ARRAY in addition to independent monitor unit calculations using RadCal; however, the study focused only on the measured dose by the ion chamber 2D-ARRAY. Figure 2 shows the plan dose calculated by TPS and Figure 3 shows the measured dose by the 2D-ARRAY.The results showed agreement between the measurement dose by the 2D-ARRAY and the calculated dose produced by the TPS. Figure 4 shows the overlap of the planned dose and the measured dose using the gamma index. Every point measured in these plans agreed to within ±3% acceptability criteria.

 Figure 2 

The chart presenting the matrix of isodose line chamber readings failing the gamma-index criterion for the planned dose by the TPS where the fractional dose is was 2.192 Gy

Int J Med Sci Image (Click on the image to enlarge.)
 Figure 3 

This chart shows the matrix of isodose lines of the measured dose by the 2D-ARRAY where the fractional dose was 2.185Gy

Int J Med Sci Image (Click on the image to enlarge.)
 Figure 4 

This chart shows the matrix of isodose compression between the planned dose in PTS and the measured dose by 2D-ARRAY ion chambers, where the matrix for the measured dose is shown in dashed lines. In this data 99% of the evaluated points passed.

Int J Med Sci Image (Click on the image to enlarge.)

All the ten selected pretreatment plans were acceptable for clinical use. The evaluation of pretreatment plans for IMRT QA is based on many factors such as patient position and patient immobilization and reproducibility; however, here we only evaluated the IMRT QA using the 2D-ARRAY ion chamber. All of our ten selected treatments plans successfully passed the gamma analysis criterion with more than 97% pixels in every defined field size for each treatment plan.

Conclusion

Patient specific dosimetric QA for IMRT plan is an important component of clinical usage of IMRT. Our result showed a very good agreement between measurements dose and calculated dose which demonstrated that our treatment planning using IMRT is accurately done compared with the dose planned by the TPS. The 2D-ARRAY ion chamber measurement agreed with the planned dose, all the plans passed with >95% gamma criterion with pixels under 5% dose difference and 3 mm distance to agreement for IMRT patient-specific quality assurance (QA). A good consistency was observed across the treatments. We concluded that using 2D-ARRAY for IMRT verification plans is a fast method and possesses all the advantages of ionization chamber dosimetry.

Acknowledgements

The author would like to express her gratitude thanks to all of our patients who participated in this study and without whom the study cannot be completed. In addition the author would like to extend her thanks to King Faisal Specialist Hospital and Research Center, Riyadh, Saudi Arabia for their continuous support. The author would like to acknowledge the professional editing assistance of Dr. Belinda Peace.

Conflict of Interest

The authors have declared that no conflict of interest exists.

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Author contact

Corresponding address Corresponding author: Dr. Huda I. Al-Mohammed, King Faisal Specialist Hospital & Research Centre, Dept. of Biomedical Physics, MBC # 03, POB 3354, Riyadh 11211, Saudi Arabia. Email: hmohamededu.sa; Tel: +966(1) 464-7272, Ext 35052


Received 2010-12-27
Accepted 2011-6-2
Published 2011-8-2