Skin Dosimetry in Breast Teletherapy on an Anthropomorphic and Anthropometric Phantom

Research Article

# Skin Dosimetry in Breast Teletherapy on an Anthropomorphic and Anthropometric Phantom

Nogueira LB¹*, Lemos Silva HL², Silva SD³ and Campos TPR³

1Anatomy and Imaging Department, Federal University of Minas Gerais, Brazil

2Santa Casa Hospital, Brazil

3Nuclear Engineering Department, Federal University of Minas Gerais, Brazil

*Corresponding author: Nogueira LB, Anatomy and Imaging Department, Federal University of Minas Gerais, 190 Alfredo Balena Avenue, zip code 30130100,Belo Horizonte, Brazil

Received: March 31, 2015; Accepted: May 19, 2015; Published: May 28, 2015

## Abstract

Keywords: Skin Dosimetry; Breast Teletherapy; Phantom and radiochromic films

## Introduction

The breast neoplasm is the most frequently diagnosed cancer in women around the world representing about 25% of all new cancer cases [1]. According to Consensus Document between the Brazilian Medical Association and the Federal Medical Council [2,3], the therapeutic modalities often used are surgery and radiotherapy for localized tumor; while, chemotherapy and endocrine therapy for systemic treatment. The main modalities used in radiotherapy are Teletherapy, provided by Cobalt therapy or linear accelerator 4-6 MV, and brachytherapy based on Low-Dose-Rate (LDR) implants of iridium-192 wires or on High-Dose-Rate (HDR) after loading Ir-192 brachytherapy [4,5].

Phantoms are physical objects or mathematical models used to reproduce the characteristics of the radiation absorption and scattering in body or body part. They are generally used to simulate the ionizing radiation transport and the dosimetry [6]. Dosimetry is the determination of absorbed dose at one point of a material medium exposed to ionizing particles [7].

Radiochromic films are used for radiation Dosimetry since 1960s. The recent improvements in technology associated with the production of these films made their use increasingly popular.

The main advantages of radiochromic films include photon tissue equivalence, high spatial resolution, linearity with absorbed dose, low energy dependency, insensitivity to visible light and no need for revelation, made them suitable for applications in quality control procedures in radiotherapy [8,9]. This work is justified by the need of measuring skin dose in patients submitted to Teletherapy. It is known that there is now a greater number of new Technologies and Planning Software’s (TPS), whose evaluation requires experimental inter comparison of the recommended prescribed doses in TPS to the absorbed doses received by the patients. It is also known that the harmful effects on the skin are still identified today in the breast radiotherapy; and, as the incidence of breast cancer has increased, it is necessary provide measurements of the skin dose, to assess changes in the current irradiation protocols. To do so, technology of the radio chromic films is a suitable tool to measure and validate the skin dose in breast radiotherapy.

## Phantoms, image generation and references marks

Thorax and breast phantoms, developed by the research group NRI /UFMG [10,11], were used as a basis for dosimetric studies. The breast phantom consists of three-Tissue Equivalent (TE’s): glandular, adipose and skin made of human elemental composition defined by ICRU-44 [12]. The images generation by Computed Tomography (CT), a GE Healthcare Hispeed CT model was used. A radio transparent support was used to hold the thorax phantom, keeping it in the same position during the CT images generation and during the irradiation of the breast phantom. Cross marks were set in the thorax phantom together with radiopaque fiducials to computer-assisted positioning in establishing the isocenter.

The conformal radiotherapy planning was performed using a series of CT images of the thorax phantom imported by the SOMAVISION program. The setup data of the radiotherapy planning were exported to CADPLAN program for generating the isodose curves. The employed method for the tissue in homogeneity correction was the modified-Batho [13], which adjusts the absorbed dose calculations through the differences in the attenuation coefficients that the primary beam undergoes in tissue compared to water. The simulated planning was based on a typical prescription for breast cancer radiotherapy with a total prescribed dose of 50.4 Gy in 28 fractions of 1.8 Gy per day, isocentric technique and filter type-15. The total calculation of the Monitor Units (MU) for the internal tangent field was 126 and 132 MU for the external tangent field; fields´ size of 7.5 cm in x-axis and 14 cm on y-axis. Angles of the collimator and gantry were 14° and 297° for the internal tangent field, respectively. For the external tangent field, both were 346° and 101°, respectively. Source-Surface Distance (SSD) was 91.4 cm and 94.1 cm for the internal and external tangential fields, respectively.

## Calibration protocols - water phantom and solid water plates

The linear accelerator VARIAN 2100C was calibrated following the protocol TRS 398 [15] such that a MU corresponded to 0.01Gy at the depth of electronic equilibrium for a 10 cm x 10 cm field and a Source-Skin Distance (SSD) of 100 cm. For dosimeter´s calibration a water phantom with 30 cm³ and solid water Gammex 457 plates with 20 x 20 cm and 4 cm thick were used.

For water phantom calibration, six 3.0 cm x 3.0 cm sealed radiochromic films were fixed on a support in to the water phantom following the direction of the central ray of the irradiation field. The vertical depths of the film were: 1.5 cm; 3.5 cm; 7.5 cm; 11.5 cm; 15.5 cm and 19.5 cm from the surface of the water. The films were irradiated simultaneously, following the standard setup of the accelerator, assuming a SSD of 100 cm and a 10 cm x 10 cm field. In this configuration, 200 MU were applied, which represents an absorbed dose of 2.0 Gy at 1.5 cm depth for a field of 10 cm x 10 cm and SSD of 100 cm. The percentage dose profile - PDP to the depths of 1.5 cm; 3.5 cm; 7.5 cm; 11.5 cm; 15.5 cm and 19.5 cm were 100.0%; 92.4%; 76.0%; 61.3%; 48.9% and 39.5%, respectively. The multiplication of the MU by PDP values determined the absorbed dose in each film in their depths.

For calibration with solid water plates, ten 3.0 x 3.0 cm sealed radiochromic films were positioned in the center of the solid water plate at 4 cm depth, SSD of 100 cm and 10 cm x 10 cm field. Ten irradiations were performed for replacing each film, covering the dose domain of 0.25 Gy to 2.5 Gy, with an interval of 0.25 Gy.

The exposed radiochromic films from both calibration protocols were digitalised by transmission scanner, model Scan get HP G4050.The RGB color components in each image were splited on its components in the ImageJ program. The RGB value of each component was settled into a range from 0 to 255, in gray level, where 255 corresponds to white and zero corresponding to the absence of colour, black. The radiation absorbed by the radio chromic film was indicated by the degree of intensity of the Red (R) and Green (G) components.

The optical densities associated with the intensity of the R and G components generated from the RGB decomposed images were evaluated as follows:

where OD is the optical density of the film; I0 represents the intensity of the R or G components in the non-irradiated film; and I represents the intensity of the R or G components intensity in the irradiated film. The standard deviation of the optical densities of sensitised and non-sensitised radiochromic films were evaluated as follows:

${\sigma }_{OD}\left(RGB\right)=\frac{1}{ln\left(10\right)}\sqrt{\frac{{\sigma }_{I}{\left(RGB\right)}^{2}+{\sigma }_{o}^{2}}{{m}_{I}{\left(RGB\right)}^{2}-m{\left(FO\right)}^{2}}+\frac{{\sigma }_{n}{\left(RGB\right)}^{2}+{\sigma }_{o}^{2}}{{m}_{n}{\left(RGB\right)}^{2}-m{\left(FO\right)}^{2}}}$

where sOD is the standard deviation of the optical density obtained from the intensities of R, G or B components from the film; s1 is the standard deviation of the averages of the R, G and B components of the irradiated film; s0 is the standard deviation of a scanned opaque film; sn is the standard deviation of the averages of the R, G or B components of the non- irradiated film; m1 is the average of the R, G or B components of the irradiated film; mn is the average of the R, G, or B components of the non-irradiated film; and m(FO) is the average of the R, G, or B components of the opaque film.

A mathematical relationship between optical density and absorbed dose percentage or absorbed dose was obtained. A linear fit was prepared on the ORIGIN program [16]; adjusting the OD values of the R component from the calibration´s films and the absorbed dose percentage or absorbed dose for each calibration method, provided by the expressions:

DP = b+a(OD) (3)

D =b’+a’(OD) (4)

in which DP represents the absorbed dose percent, D represents absorbed dose, b and b’ the intercept of the straight line on the ordinate axis, a and a’ the slope of the straight line, OD the optical density. We also performed the intensity´s readings of not-sensitised and sensitised films to identify the maximum value of R, B, and G components.

## Dosimetry of the TE skin

After irradiation of the breast phantom, sensitized films were removed of their sealing and scanned in transmission scanner model HP Scanget G4050. The digitalized images were decomposed into their R, G, and B components through of the ImageJ program, saved on ASCII files. The R-component data were converted into the optical density applied to each pixel, according to equation (1). It preserved the spatial distribution of the absorbed dose. The standard deviation was calculated according to equation (2). The optical density values were converted to the absorbed dose percent or absorbed dose by equation (3) or (4), in intervals of 0.1 Gy and transformed into surface graphs. Absorbed doses in radiochromic films positioned over the synthetic skin were analyzed. Comparison between the two irradiation of the breast phantom and between the two calibration protocols was performed.