Journal of Medical Physics
: 2019  |  Volume : 44  |  Issue : 2  |  Page : 91--98

Clinical evaluation of a two-dimensional liquid-filled ion chamber detector array for verification of high modulation small fields in radiotherapy

Miljenko Markovic1, Ganesh Narayanasamy2, Sotirios Stathakis1, Panayiotis Mavroidis3, Ines-Ana Jurkovic1, Daniel Saenz1, Niko Papanikolaou1,  
1 Department of Radiation Oncology, University of Texas Health San Antonio, San Antonio, TX, USA
2 Department of Radiation Oncology, University of Arkansas for Medical Sciences, Little Rock, AR, USA
3 Department of Radiation Oncology, University of North Carolina, Chapel Hill, NC, USA

Correspondence Address:
Dr. Miljenko Markovic
Department of Radiation Oncology, University of Texas Health San Antonio, 7979 Wurzbach Rd, San Antonio, TX 78229


Introduction: Clinical evaluation of a two-dimensional (2D) liquid-filled ion chamber detector array used in the verification of highly modulated small beams of stereotactic body radiation therapy (SBRT) has been conducted. Materials and Methods: Measurements with the Octavius 1000 SRS (PTW, Freiburg, Germany) detector with 977 liquid-filled ion chambers were compared against EDR2 film and PTW Octavius Seven29. The performance of detector array has been evaluated on ten SBRT patient plans. Dose profiles of individual and composite fields' calculated using Pinnacle3 treatment planning system were compared against measurements with Octavius 1000 SRS detector array, EDR2 film, and Octavius Seven29 detector. Gamma index and profile comparison were used in the evaluation and assessment of the detector's performance. Results: The Gamma index measurements show agreement between Pinnacle3 computations and Octavius 1000 SRS array, PTW Octavius Seven29, and EDR2 film for >90% of the points using 2%, 2 mm tolerance criteria. Profiles obtained with the Octavius 1000 SRS were in agreement with the EDR2 film profiles, demonstrating the detector's superior sampling rate. Conclusions: The Octavius 1000 SRS is a dosimetrically accurate device to perform quality assurance checks in SBRT treatments. The broad range of measurements performed in this study quantified the dosimetric accuracy of Octavius 1000 SRS detector in the clinical setup of the small fields in radiotherapy.

How to cite this article:
Markovic M, Narayanasamy G, Stathakis S, Mavroidis P, Jurkovic IA, Saenz D, Papanikolaou N. Clinical evaluation of a two-dimensional liquid-filled ion chamber detector array for verification of high modulation small fields in radiotherapy.J Med Phys 2019;44:91-98

How to cite this URL:
Markovic M, Narayanasamy G, Stathakis S, Mavroidis P, Jurkovic IA, Saenz D, Papanikolaou N. Clinical evaluation of a two-dimensional liquid-filled ion chamber detector array for verification of high modulation small fields in radiotherapy. J Med Phys [serial online] 2019 [cited 2019 Jun 24 ];44:91-98
Available from:

Full Text


Stereotactic body radiation therapy (SBRT) technique is being used routinely, often in combination with intensity-modulated radiotherapy (IMRT). In this context, SBRT uses very small-sized field to deliver a large radiation dose with steep dose gradient, necessitating dose calculations involving small field dosimetry. Higher doses with smaller fields introduce more uncertainty into modeling in the treatment planning system (TPS), treatment planning calculations, patient-specific quality assurance (QA) measurements, and treatment delivery. Therefore, to perform treatments, which will not damage the healthy tissues surrounding the target and achieve reliable dose delivery to the target volume, spatial, and dosimetric accuracy of the delivered dose distribution is required. A number of studies[1],[2],[3],[4] have pointed out the use of small fields for precisely targeting of treatment volumes have clinical advantages but bears many challenges that need to be addressed.[5]

QA and verification of the delivered dose[6],[7],[8],[9] for such complex treatments are necessary. Several reports[10],[11],[12] have recommended implementation protocols for radiotherapy treatment planning as well as specific software tools and measurement devices for clinical verification of patient-specific IMRT QA.[13],[14],[15] The small field measurements require precise and accurate placement of the detector at the center of the field and depth of interest, failing which may lead to measurement error due to placement uncertainties.[16] A high sampling frequency necessitates closer placement and smaller detector volume, both of which have the Nyquist frequency limitations. The sensitivity of an ion chamber depends on the density of the active media and for a liquid-filled chamber and it is up to three orders of magnitude higher than that of an air-filled ion chamber of the same sensitive volume. This led to a significant reduction in detector volume and allows closer placement of ion chambers for higher sampling frequency. Catano et al.[17] investigated a liquid-filled ionization chamber for high-precision relative dosimetry and showed its ability to perform profile measurements and penumbrae determination with excellent accuracy. Pardo et al.[18] investigated the verification of intensity-modulated profiles using a pixel segmented liquid-filled ion chamber linear array and concluded that good repeatability, small pixel size, and high spatial resolution make the detector ideal for profile verification of high-gradient beams utilized in IMRT and SBRT. Pena et al.[19] investigated the temperature dependence of the liquid-filled ionization chamber and Mosquera et al.[20] investigated that the ionic recombination and free-ion yield observed in liquid-filled isooctane.

QA of volumetric modulated arc therapy plan formulates the necessity to study the angular dependence of the detector array. The changes in the beam direction intercepting the detector plane characterize the angular dependence of the detector. It is observed that the array measurements underestimate the dose on the beam axis for the open field half-arc deliveries.[21] The angular dependence of the single detector at the center of the Octavius 1000 detector array has been investigated.[22] To determine the correction factors for the single detector as well as for the array of detectors is a complex process. The development of the PTW Octavius 4D phantom that comes with an inclinometer (attachable to the gantry) minimizes the need for angular dependence correction since during the delivery two-dimensional (2D) array is always perpendicular to the beam axis. For the verification of high-gradient beam profiles, volume effect[22] of the detectors is an important characteristic for the accurate representation of the measured dose profiles.

The present investigation evaluates a 2D liquid-filled ion chamber detector array for planar dose measurements of clinical radiation beams. The detector array has a limited field size with high-spatial resolution suitable for small field dosimetry and can find a utility in patient-specific QA of SBRT targets. Gamma analysis of the measured data against TPS calculation has been reported but may lack sensitivity in highly-modulated fields. In addition to gamma analysis, beam profiles have been displayed.

 Materials and Methods

The dosimetric characteristics of the 2D liquid-filled ion chamber detector array Octavius 1000 SRS (PTW, Freiburg, Germany) are investigated in this study. The 2D detector array consists of 977 liquid-filled ionization chambers arranged in a square plane and span over an area of 11 cm × 11 cm. Each detector has a size of 2.3 mm × 2.3 mm × 0.5 mm (volume = 2.65 mm3). In the inner high-resolution area of 5.5 cm × 5.5 cm2, the center-to-center spacing of the detectors is 2.5 mm, whereas the center-to-center spacing of the detectors in the outer area is 5 mm.

The linear dimensions of the 2D Octavius 1000 SRS are 30 cm width × 42 cm depth × 2.2 cm height and weight approximately 5.4 kg. According to the manufacturer, the reference point is located 9 mm below the surface of the array. The device is able to measure absorbed dose and absorbed dose rate to water. A correction factor for daily output variation of the linac was performed by measuring the dose with an ADCL calibrated air field ionization chamber and the detector array under the same conditions. The Octavius 1000 SRS uses PTW's VeriSoft software ver 5.1 (PTW, Freiburg, Germany) for measurement acquisition and data analysis which includes profile comparison (horizontal, vertical, and diagonal), planar isodose overlay, and gamma index calculation.

PTW's 2D-Array Seven29 vented ion chamber array used for comparison consists of 729 vented ionization chambers uniformly arranged over an area of 27 cm × 27 cm. The vented plane-parallel ion chambers are cube-shaped (5 mm × 5 mm × 5 mm), and the center-to-center spacing is 10 mm. The array has 2.2-cm thickness, and chambers are surrounded by acrylic. The VeriSoft software, the same version used with Octavius 1000 SRS, controls the detector. An on-site correction factor for the quality of the beam and daily output variation of the linac was measured under the same conditions as described above and applied during measurements.

Kodak EDR2 film (Carestream Health, Rochester, NY) was used for comparison in this study due to its high spatial resolution. The films were calibrated before each comparison to obtain delivered dose using a series of film exposures at known doses. The optical density for each dose level was then used to create a calibration curve which was applied to convert the film measurements to delivered dose.

A Novalis Radiosurgery platform (Brainlab AG, Feldkirchen, Germany) linear accelerator equipped with 120 high definition multi-leaf collimator (HD-MLC) was used in all the measurements of this study using 6 MV photon beams.

Patient selection

Ten most-recent SBRT patient plans were used for all measurements in this study. All the plans were optimized using the Pinnacle3 (Philips, Madison, WI) TPS. Each plan was optimized to deliver the dose to the target using eight to eleven static IMRT fields. The treatment site, dose, and field statistics are shown in [Table 1]. After the optimization and approval of each plan, the dose distributions of each field and the composite dose distribution from the summation of all the beams was calculated on the CT image set of the phantom. Phantom irradiation was performed as displayed in [Figure 1] and [Figure 2].{Table 1}{Figure 1}{Figure 2}

Phantom setup

One set of measurements was conducted for the dose profiles comparison of the Octavius 1000 SRS detector array resolution with EDR2 film. [Figure 1]a shows the setup of the Octavius 1000 SRS used throughout the first set of measurements. Plastic Water Phantom material (CNMC, Nashville, TN) was used for the buildup and backscatter of radiation. The plastic water slabs used are plates of a 30 cm × 30 cm surface size, of various thicknesses, with a density of 1.03 g/cm3. The thickness of the buildup slab was 4.1 cm, and the thickness of the backscatter slab was 5 cm. The source to surface distance for the measurement setup was 95 cm such that the reference point of measurement of the Octavius 1000 SRS was set to be at source to detector distance (SDD) of 100 cm. Results from the individual fields measured using the Octavius 1000 SRS detector was compared with EDR2 film measurements performed at 100 cm SDD [Figure 1]b.

The second set of measurements was performed for the comparison of the dose profiles while changing the buildup thickness. The octagon-shaped Octavius solid-body phantom demonstrates change in sensitivity with depth[23] when using different buildup thickness during measurement. As shown in [Figure 2]a and [Figure 2]b, Octavius 1000 SRS, Octavius Seven29 arrays and EDR2 film were irradiated using PTW's Octavius phantom such that SDD was 100 cm using 15 cm buildup. The Octavius 1000 SRS and Seven29 detector profiles were compared against EDR2 film profiles. The Octavius phantom (PTW, Freiburg, Germany) is made of polystyrene (density of 1.04 g/cm3) which acts as both buildup and backscatter material. A similar, energy-dependent correction factor for Seven29 was measured and applied to each measurement.

Finally, patient-specific IMRT QA measurements were carried out to compare the treatment planning calculated planar composite doses of each plan against measurements with the Octavius 1000 SRS, the EDR2 film and the Octavius Seven29 using the Octavius phantom setup as shown in [Figure 2].

Gamma analysis

For dosimetric comparison, gamma analysis was performed on planar dose profile using two sets of criteria: 2% dose difference (DD), 2 mm distance-to-agreement (DTA) and 3% DD, 3% DTA. A dose threshold of 10% of the global maximum measured dose was applied to discard contribution of low dose region in the analysis.

Statistical analysis

Pairwise correlation coefficient and statistically significant differences were ascertained among the various measured, and TPS computed data using STATA R9 (College Station, TX, USA). Normality of the data was tested using the Shapiro–Wilk test using threshold of 0.05. For normally distributed data, Student's t-test was applied, and the Wilcoxon signed-rank test was employed otherwise.


[Figure 3] shows the results of measurements for the several fields used for comparison between Octavius 1000 SRS array and EDR2 film using the setup shown in [Figure 1]. The number of monitor units delivered per field ranged from 405 (lung plan) to 528 (liver plan) while the number of segments per fraction ranged from 8 to 20, respectively. The agreement between the Octavius 1000 SRS and EDR2 film-measured profiles for high- and low-modulated fields with the gamma index ranging from 91% to 95% for all measured fields based on 2% DD, 2-mm DTA and higher than 95% for 3% DD, 3-mm DTA criteria. The Octavius 1000 SRS data follow closely the film-measured profiles.{Figure 3}

[Figure 4] shows the results of the comparisons for several fields between Octavius 1000 SRS, Octavius Seven29 and EDR2 film using the setup shown in [Figure 2] for single field analysis. The respective comparison of the profiles measured with Octavius Seven29 and film illustrate the advantage of the high spatial resolution and sampling capabilities of the Octavius 1000 SRS. Using the Octavius Seven29 the gamma index ranged between 91% and 100% for all measured fields using the 3%, 3 mm criteria. It is apparent that due to the limited number of points of the Octavius Seven29, the spatial information of the dose profile were lower. Highly-modulated regions serve as good examples of the importance of high-resolution detectors for an accurate and meaningful representation of such modulated fields.{Figure 4}

The measured planar doses of the composite plan were finally compared [results of several fields are shown in [Figure 5] between Octavius 1000 SRS, Octavius Seven29, and EDR2 film using the setup shown in [Figure 2]. The number of monitor units delivered per fraction ranged from 456 to 4322, and the number of segments ranged from 110 to 270. The agreement between the Octavius 1000 SRS and the film-measured profiles using the gamma index was between 93% and 100% for all measured fields (using 3% and 3 mm criteria).{Figure 5}

[Table 2] tabulates results from gamma comparison of the Octavius 1000 SRS with EDR2 film, treatment plan, and Seven29 measurements. The measurements were performed at depths of 5 and 15 cm, as outlined in [Figure 1] and [Figure 2], respectively. The Octavius 1000 SRS data matched well with the film-measured profiles exhibiting once again the accuracy of the detector and its ability to capture the steep dose variation for highly-modulated fields, especially when contrasted to the Octavius Seven29.{Table 2}

Pairwise correlation between Octavius 1000 SRS, EDR2 film, Octavius Seven29 measured dat, and the Pinnacle3 calculated data yielded Pearson correlation coefficient >0.98. Two-tailed paired Student's t-test returned P > 0.1 between the measurements and calculated data indicating the acceptance of the null hypothesis.


In this work, the clinical application of a 2D liquid-filled ion chamber detector array, the Octavius 1000 SRS is investigated. The Octavius 1000 SRS is found to be easy to use for pre-treatment delivery verification in radiotherapy. The setup procedures and experimental positioning are simple and straightforward. Three different sets of measurements for small fields of highly-modulated beams were performed in this study. Although the detector is available for QA of SRS/SBRT treatment plans, we focused on SBRT applications considered to be appropriate based on the detectors resolution and capability to accurately resolve dose profiles across the field as well as across the single detector considering changes in energy spectrum with a depth of measurement.

In the first set of measurements outlined in [Figure 1], a comparison between the Octavius 1000 SRS and EDR2 film measured profiles was performed for single field exposure and 5 cm slab phantom. The center to center spacing of 2.5 mm (sampling frequency 0.4 mm−1) between the ion chambers produces a sampling rate, which results in an accurate representation of the measured profiles of highly-modulated fields. Using the gamma criterion with tolerances of 3% and 3 mm, the percentage of the points passed ranged from 95% to 100%. Person correlation coefficient >0.99 confirms high degree of association between the two data sets. In a similar dosimetric study, Poppe et al.[24] found 98.4% passing rate for 3% and 3 mm gamma index evaluation between Octavius 1000 SRS and Gafchromic ETB3 film for IMRT fields from the prostate treatment plan. Gamma criterion with tolerances of 2% and 2 mm has a passing rate ranging from 91% to 95% for the same fields delivered. There are several factors impacting the outcome of the change in the gamma criterion. Sampling frequency 0.4 mm−1 (Octavius 1000 SRS) vs. 11.2 mm−1 (EDR2) corresponds to approximately 28 sampling points for the length of a single ion chamber in the detector array. Low and Dempsey[25] evaluated the gamma dose distribution comparison method with maximum dose gradient of 12% mm−1 and pixel spacing of 1 mm. While the pixel spacing of the evaluated dose response was sufficiently small to provide accurate calculation of gamma in the steep dose gradient regions, the surface area (2.3 mm × 2.3 mm) of a single detector carries a complexity on its own. Even though the dose-response function of the single chamber cross-section has relatively small σ value of the Gaussian does-response function (0.72 mm),[24] the volume averaging effect[23] becomes more obvious when lowering the % dose difference, distance to agreement criteria for gamma index calculation. The positional errors during the setup,[23] temperature dependence of the liquid-filled ionization chamber,[20] and errors with film processing[26],[27],[28],[29],[30] also contribute to the uncertainty of the measured data.

The second set of measurements was performed at varying depths, where single field exposures were compared between the Octavius 1000 SRS, Octavius Seven29 and EDR2 film. Previous research[23] investigated the sensitivity of the detector with the change in buildup thickness. At shallow depths, change in sensitivity can be attributed predominantly to the lower energy charge particles produced by the collimation system. A large variation in array signal to small changes in geometry at larger depths is dominated by alteration in the energy spectrum with depth. Practical use of the detector array on a daily basis will most likely include phantom buildup of the thickness we considered in the study as “higher depth.” Highly-modulated field profiles acquired with 1000 SRS detector array closely follow the profiles acquired by the EDR2 film, as displayed in [Figure 3] with the Pearson correlation coefficient >0.98. The sensitivity change with depth showed minimal impact on the data measured and compared to EDR2 film [examples shown in [Figure 6] as well as on the single detector point comparisons with the Octavius Seven29. The profile comparison between the Octavius Seven29 and film showed the importance of detector spatial resolution and the advantage of Octavius 1000 SRS. Although the single point agreement of the detector Seven29 with film could be considered acceptable (between 91% and 100% for the 3% 3 mm criteria), due to the limited number of sampling points along the axis of the detector, the complete representation of the modulated profile is not achievable [Figure 7] without increasing the sampling rate.[13] With a 5 mm shift, the sampling frequency is doubled (0.2 mm−1), yet in case of highly modulated beams with steep gradients, the spatial resolution will be compromised due to the size of the single detector and its volume averaging effect (not taking into account possible setup errors).{Figure 6}{Figure 7}

A third set of measurements was performed using multiple field irradiations on Octavius phantom with Octavius 1000 SRS, Octavius Seven29, and EDR2 film. Although the single detector of the Octavius 1000 SRS array can detect submillimetric changes in the field, any variation in the intensity along the single detector will not have an adequate spatial resolution. Detailed analysis into these issues is outside our scope.

The present results verify the argument that the complete representation of the modulated profile cannot be achieved without increasing the sampling rate. Multiple field exposures at high doses delivered to the Octavius 1000 SRS showed the response of the detector to be almost identical to those of EDR2 film and Octavius Seven29. This finding shows there is a linear relationship between the responses of Octavius 1000 SRS with doses in the clinical range.


Based on the measurements and data analysis of this study, the Octavius 1000 SRS was found to be a dosimetrically accurate array detector suitable for QA and verification of SBRT treatments in radiotherapy. An array of detectors with fine size and high spatial resolution are equally capable of representing the dose profiles of highly-modulated fields as films. The variety of the phantoms and setup used did not produce significant changes in the accuracy of the measurements. Accuracy of the detector array for usage not only for dosimetric verification of patient plans but also in the QA of the linear accelerator. In future studies, we will focus on evaluating detector performance in solely SRS treatments and flattening filter free applications.

Financial support and sponsorship


Conflicts of interest

There are no conflicts of interest.


1Webb S. Intensity Modulated Radiation Therapy. Bristol (England): Institute of Physics Publishing; 2000.
2Zelefsky MJ, Fuks Z, Hunt M, Yamada Y, Marion C, Ling CC, et al. High-dose intensity modulated radiation therapy for prostate cancer: Early toxicity and biochemical outcome in 772 patients. Int J Radiat Oncol Biol Phys 2002;53:1111-6.
3Kam MK, Chau RM, Suen J, Choi PH, Teo PM. Intensity-modulated radiotherapy in nasopharyngeal carcinoma: Dosimetric advantage over conventional plans and feasibility of dose escalation. Int J Radiat Oncol Biol Phys 2003;56:145-57.
4Krueger EA, Fraass BA, McShan DL, Marsh R, Pierce LJ. Potential gains for irradiation of chest wall and regional nodes with intensity modulated radiotherapy. Int J Radiat Oncol Biol Phys 2003;56:1023-37.
5Paskalev KA, Seuntjens JP, Patrocinio HJ, Podgorsak EB. Physical aspects of dynamic stereotactic radiosurgery with very small photon beams (1.5 and 3 mm in diameter). Med Phys 2003;30:111-8.
6Galvin JM, Bednarz G. Quality assurance procedures for stereotactic body radiation therapy. Int J Radiat Oncol Biol Phys 2008;71:S122-5.
7Poppe B, Blechschmidt A, Djouguela A, Kollhoff R, Rubach A, Willborn KC, et al. Two-dimensional ionization chamber arrays for IMRT plan verification. Med Phys 2006;33:1005-15.
8Martens C, De Wagter C, De Neve W. The value of the LA48 linear ion chamber array for characterization of intensity-modulated beams. Phys Med Biol 2001;46:1131-48.
9Spezi E, Angelini AL, Romani F, Ferri A. Characterization of a 2D ion chamber array for the verification of radiotherapy treatments. Phys Med Biol 2005;50:3361-73.
10Kutcher GJ, Coia L, Gillin M, Hanson WF, Leibel S, Morton RJ, et al. Comprehensive QA for radiation oncology: Report of AAPM radiation therapy committee task group 40. Med Phys 1994;21:581-618.
11Poppe B, Djouguela A, Blechschmidt A, Willborn K, Rühmann A, Harder D. Spatial resolution of 2D ionization chamber arrays for IMRT dose verification: Single-detector size and sampling step width. Phys Med Biol 2007;52:2921-35.
12Fraass B, Doppke K, Hunt M, Kutcher G, Starkschall G, Stern R, et al. American association of physicists in medicine radiation therapy committee task group 53: Quality assurance for clinical radiotherapy treatment planning. Med Phys 1998;25:1773-829.
13Low DA, Harms WB, Mutic S, Purdy JA. A technique for the quantitative evaluation of dose distributions. Med Phys 1998;25:656-61.
14Tsai JS, Wazer DE, Ling MN, Wu JK, Fagundes M, DiPetrillo T, et al. Dosimetric verification of the dynamic intensity-modulated radiation therapy of 92 patients. Int J Radiat Oncol Biol Phys 1998;40:1213-30.
15Boehmer D, Bohsung J, Eichwurzel I, Moys A, Budach V. Clinical and physical quality assurance for intensity modulated radiotherapy of prostate cancer. Radiother Oncol 2004;71:319-25.
16Li S, Rashid A, He S, Djajaputra D. A new approach in dose measurement and error analysis for narrow photon beams (beamlets) shaped by different multileaf collimators using a small detector. Med Phys 2004;31:2020-32.
17González-Castaño DM, Gómez F, Brualla L, Roselló JV, Planes D, Sánchez M, et al. Aliquid-filled ionization chamber for high precision relative dosimetry. Phys Med 2011;27:89-96.
18Pardo J, Roselló JV, Sánchez-Doblado F, Gómez F. Verification of intensity modulated profiles using a pixel segmented liquid-filled linear array. Phys Med Biol 2006;51:N211-9.
19Pena J, Franco L, Gomez F, Iglesias A, Pardo J, Pazos A, et al. Liquid-filled ionization chamber temperature dependence. Nucl Instrum Methods Phys Res 2006;560:584-8.
20Pardo J, Franco L, Gómez F, Iglesias A, Lobato R, Mosquera J. Free ion yield observed in liquid isooctane irradiated by gamma rays. Comparison with the Onsager theory. Phys Med Biol 2004;49:1905-14.
21Van Esch A, Clermont C, Devillers M, Iori M, Huyskens DP. On-line quality assurance of rotational radiotherapy treatment delivery by means of a 2D ion chamber array and the octavius phantom. Med Phys 2007;34:3825-37.
22Markovic M, Stathakis S, Mavroidis P, Jurkovic IA, Papanikolaou N. Characterization of a two-dimensional liquid-filled ion chamber detector array used for verification of the treatments in radiotherapy. Med Phys 2014;41:051704.
23Laub WU, Wong T. The volume effect of detectors in the dosimetry of small fields used in IMRT. Med Phys 2003;30:341-7.
24Poppe B, Stelljes TS, Looe HK, Chofor N, Harder D, Willborn K, et al. Performance parameters of a liquid filled ionization chamber array. Med Phys 2013;40:082106.
25Low DA, Dempsey JF. Evaluation of the gamma dose distribution comparison method. Med Phys 2003;30:2455-64.
26Dogan N, Leybovich LB, Sethi A. Comparative evaluation of Kodak EDR2 and XV2 films for verification of intensity modulated radiation therapy. Phys Med Biol 2002;47:4121-30.
27Chungbin S, Ezzell G. Streamlined IMRT patient verification measurements using Kodak extended dose range film (EDR2). Med. Phys 2001;28:1208-9.
28Ezzell GA, Chungbin S. The overshoot phenomenon in step-and-shoot IMRT delivery. J Appl Clin Med Phys 2001;2:138-48.
29Shi C, Papanikolaou N, Yan Y, Weng X, Jiang H. Analysis of the sources of uncertainty for EDR2 film-based IMRT quality assurance. J Appl Clin Med Phys 2006;7:1-8.
30Das I, Cheng CW, Pai S. Basic Film Dosimetry. Med. Phys 1998;25: 2093-115.