Advanced electron density phantom

Manufactured by Sun Nuclear

Sourced in United States

The Advanced Electron Density Phantom is a laboratory instrument designed to measure and analyze the electron density of various materials. It serves as a tool for calibrating and verifying the accuracy of medical imaging equipment, such as CT scanners, that rely on electron density measurements. The phantom provides a standardized reference for evaluating the performance and consistency of these imaging systems.

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Lab products found in correlation

Zebra, by IBA Dosimetry (1 mentions)

5 protocols using advanced electron density phantom

Calibrating CT Phantom for Tissue Density

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A large-diameter CT-ED table phantom (Advanced Electron Density Phantom; SUN NUCLEAR) was used to measure the CT values and image noise of the various materials. The rods of the Advanced Electron Density Phantom mimic water, cortical/inner bone, lung, and liver. They are highly equivalent to the medical standards for human tissue densities and can optimally convert CT values to electron density. Figure 5 shows an overview and analytical view of the phantom. In this study, 10 materials were used, ranging from the lung (electron density: 0.288 c/cm³) to the cortical bone (electron density: 1.774 c/cm³). Moreover, regions of interest (ROI) of mimicked water (electron density: 0.999 c/cm³) were created at the top, bottom, left, and right sides for analysis. The ROI size used in the analysis was approximately 300 mm², and the ROI was set at the center of each material. CT values and variations (SD) within the ROI were analyzed. The analysis was performed using the viewer provided with the CT device. The CT value is the mean of the CT values within the specified ROI, The SD is the analysis of the variations (1σ) of CT value within the ROI.Figure 5

Overview (left) and analytical view (right) of CT-ED table phantom.

Yasui K., Saito Y., Ito A., Douwaki M., Ogawa S., Kasugai Y., Ooe H., Nagake Y, & Hayashi N. (2023). Validation of deep learning-based CT image reconstruction for treatment planning. Scientific Reports, 13, 15413.

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Tissue-Equivalent CT Phantom Comparison

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For in vitro comparison of scan protocols, a tissue-equivalent CT to electron density calibration phantom (Advanced Electron Density Phantom; Sun Nuclear Corporation; Melbourne, FL, USA) was scanned. The 30 cm × 40 cm phantom possesses an oval shape and an effective diameter of 34.64 cm [17 (link)]. Both a SECT and DECT scan protocol were used for image acquisition. Detailed scan parameters of both scan protocols are displayed in Table 1. Standardized regions of interest (ROIs) with a diameter of 20 mm were positioned and image noise was measured in four different tissue inserts (water, fat, lung, and bone). Repeated measurements were averaged across five consecutive slices and image noise was determined by standard deviation of the mean attenuation in Hounsfield units (HU).

Huflage H., Kunz A.S., Hendel R., Kraft J., Weick S., Razinskas G., Sauer S.T., Pennig L., Bley T.A, & Grunz J.P. (2023). Obesity-Related Pitfalls of Virtual versus True Non-Contrast Imaging—An Intraindividual Comparison in 253 Oncologic Patients. Diagnostics, 13(9), 1558.

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Proton Dose Verification using 2D Array

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A set of randomly‐chosen tissue‐equivalent inserts from the Sun Nuclear Advanced Electron Density Phantom was positioned on top of a 30 × 30 × 2 cm³ water‐equivalent slab (Solid Water HE, Sun Nuclear Corporation, Melbourne, FL, USA). This phantom is shown in the left panel of Figure 2. SECT and SPR images of this phantom were obtained and used in the TPS to calculate dose distributions (2 mm dose grid resolution and 0.5% uncertainty using the Monte Carlo v5.0 algorithm) using the treatment fields for a randomly selected set of three previously‐treated patients as well as a single low energy (79.8 MeV) 20 × 20 square field of spots uniformly spaced by 2.5 mm and using 0.5 MU per spot. This single low energy was chosen to generate a homogeneous dose distribution at the measurement plane of the 2D array used to measure the distribution. The right panel of Figure 2 shows an example of the dose distribution obtained in the TPS for the square field.
Each of the selected fields were delivered to a 2D ion chamber array (Octavius 1500XDR, PTW Freiburg GmbH, Freiburg, Germany) and compared to both the SECT and SPR predicted doses. In addition to our clinical proton gamma criterion of (3%, 3 mm), the pass rates were also recorded using (1%, 1 mm) and (2%, 2 mm) criteria.

Sarkar V., Paxton A., Su F., Price R., Nelson G., Szegedi M., James S.S, & Salter B.J. (2023). An evaluation of the use of DirectSPR images for proton planning in the RayStation treatment planning software. Journal of Applied Clinical Medical Physics, 24(5), e13900.

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Validating SPR from SECT Phantoms

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As a first experiment, SECT and SPR data sets of two phantoms were obtained. The phantoms used were the Advanced Electron Density Phantom (Sun Nuclear Corporation, Melbourne, FL, USA) and Model 062 Electron Density Reference Phantom (CIRS, Norfolk, VA, USA). For each phantom, both datasets were imported into the TPS and rigidly registered to each other. Each tissue‐equivalent insert was contoured on the SECT dataset and copied onto the SPR images. From the SECT dataset, the average CT number in HU within each tissue insert was obtained. The clinical CT‐number‐to‐mass‐density curve was used to convert this to an average mass density, which was then converted to an average SPR using data provided by RaySearch Laboratories. This workflow was meant to reproduce what happens within the TPS whenever SECT is used for proton therapy dose calculations. These values are then compared to the average SPR within the corresponding regions in the SPR data set as well as the SPR for each tissue surrogate plug. The latter was determined experimentally by sending a single beam of protons of two different energies (164.8 MeV and 227 MeV) through the long axis of each plug and measuring the distal 90% range of the exiting proton beam using a Zebra (IBA dosimetry GmbH, Schwarzenbruck, Germany) multi‐layer ion chamber (MLIC).

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Calibrating CBCT Imaging Density

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The Advanced Electron Density Phantom (Model 1467, Sun Nuclear Corporation, Melbourne, FL) was used to generate the HU-ED curve for FDK-CBCT and iCBCT, as shown in Fig. 1a. The phantom consisted of inner (diameter = 20 cm) and outer (40 cm wide and 30 cm long) sections surrounded by water-equivalent material, which allowed the simulation of the x-ray scatter conditions in the pelvis. This phantom, which contained 2.85 cm diameter inserts representing the lung lymph node, adipose, breast, brain, liver, and inner bone, was correctly set up on the central axis of TrueBeam Edge, and CBCT scans were performed. Further, CBCT scans were also performed when 10 cm of the solid water (SW) was added to either end of the phantom to ensure the scatter condition simulated the patient environment. These reconstructed images were transferred to Eclipse for image analysis (Fig. 1b). Circular regions of interest (ROIs) with a 2-cm diameter were placed at the center of each reference material on FDK-CBCT images. These ROIs were copied and pasted on the iCBCT images to measure mean HU values and establish HU-ED curves. The HU-ED curves established for FDK-CBCT and iCBCT were defined as HU-ED FDK and HU-ED iCBCT , respectively. The HU-ED FDK and HU-ED iCBCT curves were set up in PerFRACTION software.

Inui S., Nishio T., Ueda Y., Ohira S., Ueda H., Washio H., Ono S., Miyazaki M., Koizumi M, & Konishi K. (2021). Machine log file-based dose verification using novel iterative CBCT reconstruction algorithm in commercial software during volumetric modulated arc therapy for prostate cancer patients. Physica medica : PM : an international journal devoted to the applications of physics to medicine and biology : official journal of the Italian Association of Biomedical Physics (AIFB), 92.

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