Original paperMegavoltage 2D topographic imaging: An attractive alternative to megavoltage CT for the localization of breast cancer patients treated with TomoDirect
Introduction
The TomoTherapy unit (Accuray, Madison, WI, USA) is a radiation therapy treatment system consisting of a 6 MeV linear accelerator that continually rotates around a patient who translates through the beam, resulting in helical fan beam delivery. TomoDirect is a radiotherapy treatment technique with fixed-angle beams performed on the TomoTherapy system [1]. Up to 12 beams can be set up at different fixed gantry angles. Each beam is delivered as the patient advances through the ring and the beam fluence is modulated by the binary multileaf collimator of the TomoTherapy system. This intensity-modulated radiation therapy (IMRT) modality has shown to be a promising treatment of the single breast, allowing better PTV dose coverage and helping to spare organs at risk compared to 3D techniques and linac-based IMRT [2], [3].
The localization of patients receiving radiation therapy for breast cancer is challenging because of the mobility of the treated area. Even with thoracic thermoplastic immobilization systems, inter-fraction positioning errors remain significant [4]. To prevent a degradation of the PTV coverage during a breast treatment with TomoTherapy, a daily pre-treatment imaging control is mandatory [5].
The TomoTherapy imaging system has been widely described in the literature [6]. It uses megavoltage-computed tomography (MVCT) and allows a 3D reconstruction of the patient's anatomy from a helical acquisition. The dose delivered to the patient during image acquisition depends on several parameters [7] and is less than 1 cGy per image if considering the coarse irradiating acquisition mode [8]. Although the doses to the organs at risk (OAR) are low in absolute value, they generate an additional risk to the patient: daily MVCT imaging would increase the risk of developing a second cancer by 33% and 63%, respectively, in the contralateral breast and lungs [9].
The theory of the TomoTherapy topographic images was presented for the first time in 2010 by Moore et al., who showed the results of using 2D topographic megavoltage images (MV2D) generated from topographic data of the TomoTherapy imager [10]. The term topographic commonly refers to scout images in conventional CT imaging: the TomoTherapy MV radiation source is placed at a fixed angulation, the patient translates with the movement of the table, and the acquisition is carried out using the TomoTherapy imager. A 2D image can then be reconstructed from the data retrieved by the imager. Kiely et al. designed a post-image process to improve the quality of MV topographic images by reducing noise and enhancing the bony anatomy [11]. Besides these theoretical studies, Takahashi studied the clinical relevance of MV2D imaging applied to a specific indication with a very long target size, total marrow irradiation (TMI) [12]. The image acquisition is much faster for MV2D than for MVCT, so MV2D can be very interesting for TMI, for which MVCT acquisition time takes ≥600 s [12]. The usefulness of MV2D imaging has never been studied in the clinical context of breast treatments: however, even though imaging acquisition time is not as decisive since the breast target volume is not so large, the dose delivered by MVCT imaging may have a significant impact, as shown previously.
The purpose of this work is to present pre-clinical characterization of MV2D imaging using phantom simulating localization of breast cancer patients treated with TomoDirect.
Section snippets
Determination of the optimal MV2D acquisition parameters
To acquire the data needed to create MV2D images, the maintenance mode of the TomoTherapy is used by the technicians (referred as the calibration mode). It is possible to vary 3 parameters: the couch speed (CS), the jaw size (JS), and the compression factor (CF) of the data generated by the detector. The CS is the speed of the couch during the acquisition of the image, and the JS describes the jaw width used to collimate the beam in the head-feet direction. We performed several dose and image
Determination of the optimal MV2D acquisition parameters
The dose measured in the TomoPhant and the acquisition time according to the CS and JS are shown in Table 2. The same measurements are given for MVCT in the normal and coarse modes.
We observed that the dose and acquisition time of the MV2D images were inversely proportional to the CS: for example, the dose went from 8.84 mGy to 2.21 mGy (at a 2 cm depth) and the acquisition time from 20 s to 5 s when the CS changed from 1 cm/s to 4 cm/s. We also observed that the dose was multiplied by a factor of
Discussion
We first note that the doses we measured for MVCT imaging correlated with those reported in the literature, either in the center or periphery of the phantom [12], [7]: the maximum deviation was about 30%, which can be explained by the variability of the measurement conditions and the impact of various parameters (vertical offset couch, scanned length, and sinusoidal shape of the dose profile) on the dose measurement [7]. The measured doses in MV2D imaging were identical to those reported in the
Conclusions
We have shown the benefit of using topographic MV2D imaging to verify the setup of breast cancer patients treated with TomoDirect. The potential for reducing doses to the heart and contralateral organs, the short acquisition time, and the ability to check the TD BEV during registration make it an alternative to MVCT. The integration of MV2D imaging for TomoDirect treatment is desirable for improving the positioning of breast cancer patients.
Conflict of interest statement
The authors have no COI to report.
Acknowledgements
We thank Isabelle Buchheit and Vincent Marchesi from ICL Nancy for the phantom lending, and Pascale, Corinne, Cyrielle, Keltoum, Matthieu, Anis and Maximilien for the MV2D and MVCT registration. We also thank Yutaka Takahashi from Osaka University for his help.
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