Dual-energy CT (DECT) utilizes two separate energy sets to examine the different attenuation properties of matter, having a significant advantage over traditional single energy CT. Independent attenuation values at two energy sets can create virtual non-contrast images from contrast-enhanced imaging as well as delineate the composition of renal calculi and arterial plaque 13.
There are different DECT technologies available:
- two x-ray tubes producing different voltages offset at approximately 90°
- single-source helical
- two spiral scans are consecutively acquired at different tube potentials.
- single-source twin-beam
- two-material filter splits the x-ray beam into high-energy and low-energy spectra on the z-axis before it reaches the patient.
- single-source sequential
- each x-ray tube rotation is performed at high- and low- tube potential.
- single-source rapid switching
- the x-ray tube switches between high- and low- tube potential multiple times within the same rotation.
- dual-layer DECT
- a "sandwich" detector absorbs high-energy photons with its top layer, and low-energy photons with its bottom layer
When an atom undergoes the photoelectric effect, the electron from that respected K-shell otherwise referred to as the inner shell is ejected via the incident photon. As that electron is excited, vacant space is 'filled' by a neighboring electron, releasing energy as a photoelectron.
In short, when a photon has sufficient energy to overcome the electron's binding energy in the K-shell, that atom undergoes the photoelectric effect.
Each substance owns a unique K-shell binding energy; known as the K-edge. There is a significant spike in attenuation that results just beyond the energy of the K-edge, this peak is unique to every material and holds valuable information about the substance's composition.
The different photoelectric energies and K-edges are the bread and butter of dual-energy CT. Although most elements in the human body have very low K-edges (0.01-0.53 keV), elements like iodine and calcium have K-edges of 33.2 keV and 4.0 keV respectively, making them sufficiently larger than surrounding structures and are particularly important in the clinical setting 1-3.
For instance, at 80 kVp a structure that contains no (introduced) iodine, such as the liver, has an attenuation based on its K-edge of x, yet when iodine (33.2 keV) is introduced into that same structure, it has a higher attenuation of y bringing it closer to 80 kVp.
As 80 kVp is closer to 33.2 keV than 140 kVp, the structures containing iodine will retain less attenuation as the kVp progressed beyond the K-edge of iodine. Therefore, when using two energies, it is possible to delineate structures based solely on their attenuation differences between 80 kVp and 140 kVp.
A dual x-ray source, tube A (140 kVp) and tube B (80 kVp or 100 kVp) with an angular offset of 90 degrees are preferred offsets for a dual source scanner in the current literature 1-5.
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Physics and imaging technology: CT
computed tomography (CT)
- CT technology
- dual energy CT
- CT image reconstruction
- CT image quality
- CT dose
CT contrast medium
- iodinated contrast media
- coronary CT angiography
- patient-based artifacts
- physics-based artifacts
- hardware-based artifacts
- CT safety
- history of CT