“…A benchtop inline phase sensitive tomosynthesis prototype was used for the acquisition of the phase sensitive projection views of the phantom. The prototype has been characterized and utilized in various biomedical imaging studies [15–18]. As shown in Figure 1(a), the prototype incorporates a micro-focus x-ray source (Model L8121-03, Hamamatsu Photonics, Japan) that consists of a tungsten (W) target with a focal spot size ranging from 7–50 μ m as its output power varies from 10–75 W. The prototype also incorporates a CMOS flat panel detector (C7942SK-25, Hamamatsu Photonics, Japan) with an active pixel sensor (APS) architecture.…”
Section: Methodsmentioning
confidence: 99%
“…Responding to these challenges, we have developed and characterized a high-energy x-ray inline phase sensitive prototype that fulfils the spatial coherence requirements as discussed in ref [9]. The prototype has shown advantages over attenuation-based imaging systems [15–18].…”
This study compared the detectability of simulated tumors using a high-energy X-ray inline phase sensitive digital breast tomosynthesis (DBT) prototype and a commercial attenuation-based DBT system. Each system imaged a 5-cm thick modular breast phantom with 50-50 adipose-glandular percentage density containing contrast-detail (CD) test objects to simulate different tumor sizes. A commercial DBT system acquired 15 projection views over 15 degrees (15d-15p) was used to acquire the attenuation-based projection views and to reconstruct the conventional DBT slices. Attenuation-based projection views were acquired at 32 kV, 46 mAs with a mean glandular dose (D) of 1.6 mGy. For acquiring phase sensitive projection views, the prototype utilized two acquisition geometries: 11 projection views were acquired over 15 degrees (15d-11p), and 17 projection views were acquired over 16 degrees (16d-17p) at 120 kV, 5.27 mAs with 1.51 mGy under the magnification (M) of 2. A phase retrieval algorithm based on the phase-attenuation duality (PAD) was applied to each projection view, and a modified Feldkamp-Davis-Kress (FDK) algorithm was used to reconstruct the phase sensitive DBT slices. Simulated tumor margins were rated as more conspicuous and better visualized for both phase sensitive acquisition geometries versus conventional DBT imaging. The CD curves confirmed the improvement in both contrast and spatial resolutions with the phase sensitive DBT imaging. The superiority of the phase sensitive DBT imaging was further endorsed by higher contrast to noise ratio (CNR) and figure-of-merit (FOM) values. The CNR improvements provided by the phase sensitive DBT prototype were sufficient to offset the noise reduction provided by the attenuation-based DBT imaging.
“…A benchtop inline phase sensitive tomosynthesis prototype was used for the acquisition of the phase sensitive projection views of the phantom. The prototype has been characterized and utilized in various biomedical imaging studies [15–18]. As shown in Figure 1(a), the prototype incorporates a micro-focus x-ray source (Model L8121-03, Hamamatsu Photonics, Japan) that consists of a tungsten (W) target with a focal spot size ranging from 7–50 μ m as its output power varies from 10–75 W. The prototype also incorporates a CMOS flat panel detector (C7942SK-25, Hamamatsu Photonics, Japan) with an active pixel sensor (APS) architecture.…”
Section: Methodsmentioning
confidence: 99%
“…Responding to these challenges, we have developed and characterized a high-energy x-ray inline phase sensitive prototype that fulfils the spatial coherence requirements as discussed in ref [9]. The prototype has shown advantages over attenuation-based imaging systems [15–18].…”
This study compared the detectability of simulated tumors using a high-energy X-ray inline phase sensitive digital breast tomosynthesis (DBT) prototype and a commercial attenuation-based DBT system. Each system imaged a 5-cm thick modular breast phantom with 50-50 adipose-glandular percentage density containing contrast-detail (CD) test objects to simulate different tumor sizes. A commercial DBT system acquired 15 projection views over 15 degrees (15d-15p) was used to acquire the attenuation-based projection views and to reconstruct the conventional DBT slices. Attenuation-based projection views were acquired at 32 kV, 46 mAs with a mean glandular dose (D) of 1.6 mGy. For acquiring phase sensitive projection views, the prototype utilized two acquisition geometries: 11 projection views were acquired over 15 degrees (15d-11p), and 17 projection views were acquired over 16 degrees (16d-17p) at 120 kV, 5.27 mAs with 1.51 mGy under the magnification (M) of 2. A phase retrieval algorithm based on the phase-attenuation duality (PAD) was applied to each projection view, and a modified Feldkamp-Davis-Kress (FDK) algorithm was used to reconstruct the phase sensitive DBT slices. Simulated tumor margins were rated as more conspicuous and better visualized for both phase sensitive acquisition geometries versus conventional DBT imaging. The CD curves confirmed the improvement in both contrast and spatial resolutions with the phase sensitive DBT imaging. The superiority of the phase sensitive DBT imaging was further endorsed by higher contrast to noise ratio (CNR) and figure-of-merit (FOM) values. The CNR improvements provided by the phase sensitive DBT prototype were sufficient to offset the noise reduction provided by the attenuation-based DBT imaging.
“…The development of specialized X-ray imaging techniques began in the 1950s to enhance imaging from the very low attenuation contrast between healthy and diseased tissues [ 32 ]. In some cases, reduced X-ray energy with increased radiation absorbance can take advantage of small differences in energy attenuation by different tissues [ 32 , 33 ].…”
Section: Medical Applications For High- and Low-let Radiationmentioning
confidence: 99%
“…The development of specialized X-ray imaging techniques began in the 1950s to enhance imaging from the very low attenuation contrast between healthy and diseased tissues [ 32 ]. In some cases, reduced X-ray energy with increased radiation absorbance can take advantage of small differences in energy attenuation by different tissues [ 32 , 33 ]. For instance, in mammography, small differences in linear attenuation by adipose and glandular tissues are optimized by using relatively low-energy X-rays, mostly below 20 KeV [ 33 ].…”
Section: Medical Applications For High- and Low-let Radiationmentioning
Exposure to ionizing radiation can occur during medical treatments, from naturally occurring sources in the environment, or as the result of a nuclear accident or thermonuclear war. The severity of cellular damage from ionizing radiation exposure is dependent upon a number of factors including the absorbed radiation dose of the exposure (energy absorbed per unit mass of the exposure), dose rate, area and volume of tissue exposed, type of radiation (e.g., X-rays, high-energy gamma rays, protons, or neutrons) and linear energy transfer. While the dose, the dose rate, and dose distribution in tissue are aspects of a radiation exposure that can be varied experimentally or in medical treatments, the LET and eV are inherent characteristics of the type of radiation. High-LET radiation deposits a higher concentration of energy in a shorter distance when traversing tissue compared with low-LET radiation. The different biological effects of high and low LET with similar energies have been documented in vivo in animal models and in cultured cells. High-LET results in intense macromolecular damage and more cell death. Findings indicate that while both low- and high-LET radiation activate non-homologous end-joining DNA repair activity, efficient repair of high-LET radiation requires the homologous recombination repair pathway. Low- and high-LET radiation activate p53 transcription factor activity in most cells, but high LET activates NF-kB transcription factor at lower radiation doses than low-LET radiation. Here we review the development, uses, and current understanding of the cellular effects of low- and high-LET radiation exposure.
“…[567] Because of their high-spatial coherence, micro-focus and synchrotron-based X-ray sources are found to be suitable for phase-contrast imaging, whereas conventional X-ray sources are not due to their low-spatial coherence. [8910] Synchrotron X-ray has several characteristics such as spatially coherent, high intensity, vertical collimation, and polarization. [1112] It is also reported that when a coherent X-ray beam gets scattered in an object it is distributed not only due to attenuation (photoelectric, absorption, and Compton and Rayleigh scatterings) but also due to refraction on the boundaries between media providing better phase-contrast visibility at boundaries.…”
Introduction:
Use of synchrotron radiation (SR) X-ray source in medical imaging has shown great potential for improving soft-tissue image contrast such as the breast. The present study demonstrates quantitative X-ray phase-contrast imaging (XPCI) technique derived from propagation-dependent phase change observed in the breast tissue-equivalent test materials.
Materials and Methods:
Indian synchrotron facility (Indus-2, Raja Ramanna Centre of Advanced Technology [RRCAT]) was used to carry out phantom feasibility study on phase-contrast mammography. Different phantoms and samples, including locally fabricated breast tissue-equivalent phantoms were used to perform absorption and phase mode imaging using 12 and 16 keV SR X-ray beam. Edge-enhancement index (EEI) and edge enhancement to noise ratio (EE/N) were measured for all the images. Absorbed dose to air values were calculated for 12 and 16 keV SR X-ray beam using the measured SR X-ray photon flux at the object plane and by applying the standard radiation dosimetry formalism.
Results and Conclusion:
It was observed in case of all the phantoms and test samples that EEI and EE/N values are relatively higher for images taken in the phase mode. The absorbed dose to air at imaging plane was found to be 75.59 mGy and 28.9 mGy for 12 and 16 keV SR energies, respectively. However, these dose values can be optimized by reducing the image acquisition time without compromising the image quality when clinical samples are imaged. This work demonstrates the feasibility of XPCI in mammography using 12 and 16 keV SR X-ray beams.
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