Presentation on theme: "Contrast Agents for CT-3 and Next Generation CT Techniques."— Presentation transcript:
Contrast Agents for CT-3 and Next Generation CT Techniques
Examples of plasmonic GNPs: 16-nm Au nanospheres; gold nanorods and gold nanorods with silver coatings (inset); SiO 2 /Au nanoshells; gold nanostars; silver nanocubes and Au-Ag nanocages obtained from them (insets); nanocomposites containing a gold nanorod or nanocage core and a mesoporous silica shell doped with hematoporphyrin; hollow mesoporous silica spheres and nanorattles containing gold nanocages; plasmonic nanopowders of gold nanospheres, nanorods, nanostars, and Au-Ag nanocages.
Spectral tuning of gold nanorods with silver coatings and Au-Ag nanocages across vis-NIR spectral bands and of gold nanorods and SiO 2 /Au nanoshells across red-NIR spectral bands. nanorod diameter (d) and length (L), nanocage edge length L and wall thickness (s), nanoshell outer diameter (d) and gold shell thickness (s).
Schematic illustration of the preparation of dendrimer-entrapped gold nanoparticles. Dendrimer-entrapped Gold Nanoparticle
CT images of mice before (a, b) and after (c, d) injection of gold nanoparticles. While little contrast enhancement is observed for the mouse administered with nonspecific immunoglobulin G (IgG)-conjugated nanoparticles (a, c), anti-CD-4-targeted nanoparticles show clear contrast enhancement of inguinal lymph nodes (c, d). Anti-CD-4-Targeted Gold Nanoparticles
(a)Kinetics of suspension laser heating for SiO 2 /Au nanoshells, Au nanorods, and Au-Ag nanocages. (b)Au-Ag nanocages and nanocomposites (nanocages with 50-nm silica coatings). Suspensions were irradiated by a diode laser at a power density of 2 W/cm 2 and a wavelength of 810 nm, which was close to the plasmon resonance wavelengths of all three particle types: SiO 2 /Au nanoshells (core diameter of 160 nm, shell thickness of 20 nm), Au nanorods (length of 40 nm, diameter of 12 nm), and Au-Ag nanocages (edge length of 54 nm).
(a) Xenografted tumor (implanted rat liver cancer cells PC-1) after the administration of AuNRs/SiO 2 -HP nanocomposites at a dose 400 μg of gold directly to the tumor before irradiation. (b) The tumor after simultaneous 20-min exposure of 633-nm CW He-Ne laser (160 mW/сm 2 ) and 808-nm CW NIR laser (2.2 W/сm 2 ). (c) 72 h after combined irradiation.
(a) Matrix metalloproteinase (MMP) activatable gold nanoparticles for dual CT/optical imaging probes. (b) CT image (middle) and NIR fluorescence image (right) of the tumor-bearing mouse 24 h after injection of the nanoparticles. Activatable Theranostic Gold Nanoparticle CTNIR
Theranostic Gold Nanoparticle
Bismuth sulfide (Bi 2 S 3 ) nanoparticles labeled with the cyclic nine amino acid peptide, CGNKRTRGC (LyP-1)-targeted to 4T1 breast cancer in mice Targeted Bismuth Nanoparticles
X-ray CT images of tumor-bearing mouse immediately (a), 2 h (b), 4.5 h (c), and 24 (d) after injection of Bi 2 S 3 nanoparticles labeled with LyP-1. In vivo micro-CT volume reconstructions post–injection polyethylene glycol 5000 coated Bi2S3 nanoparticles that do not contain a peptide label.
Serial CT Imaging
(i) A portion of X-rays is transmitted without interaction. (ii) The energy of the incident X-ray is absorbed by an atom, and then X-ray with the same energy is emitted with a random direction (Coherent scattering). (iii) When the incident X-ray collides with outer-shell electrons, a portion of the X- ray energy is transferred to the electron, and the X-ray photon is deflected with a reduced energy (Compton scattering). (iv) When the incident X-ray transfers its energy to inner-shell electron, the electron is subsequently ejected, and the vacancy of the electron shell is filled by outer- shell electrons, producing a characteristic X-ray (Photoelectron effect). Interactions of X-ray with matters
(a) Schematic drawing of third-generation CT. CT images are acquired during the rotation of an X-ray tube and an array of detectors. (b) Schematic attenuation profiles of voxels. Measured X-ray intensity can be expressed as sum of the attenuation along the path of X-ray. Spectra CT
18 Spectral/multi energy CT has the potential to distinguish different materials by K-edge characteristics. K-edge imaging involves the two energy bins on both sides of a K-edge. Energy discriminating photon counting detectors Advanced Detector Technology
19 Mass attenuation coefficients of several materials as function of X-ray energy Excitation of a 1s electron occurs at the K- edge, while excitation of a 2s or 2p electron occurs at an L-edge
Spectral CT with Energy-Resolving Detector Energy-resolving detectors discriminate colors Spectral CT with energy-resolving detector is like the human eye at day Total attenuation energy Compton Scatter Photo-electric
Emerging Opportunities with Spectral CT Multicolored or spectral CT has the potential to detect and quantify intraluminal fibrin presented by ruptured plaque in the context of CT angiograms all without calcium interference. Philips Research, Hamburg, DE Relevant Patents: US ; (Philips)
Clinical Significance of Spectral CT wiki.medpedia.com/Coronary_Calcium_Scan Negative predictive value of CT angiography established early (non- reimbursable) Poor anatomic correlation with cath Cost Inability to separate coronary Ca CORE-64 at the AHA scientific sessions (2007), noninvasive 64-slice MDCT angiography was reported to have a 91% positive and 83% negative predictive value in a large multicenter trial: 89/405 patients were excluded due to high calcium scores Poor anatomic correlation between CCTA and Cath.
Coronary Thrombus Imaging by Spectral CT Nanobeacons (Au, Bi,…) bind to fibrin Conventional CT is unable to selectively image materials Spectral CT enables material specific imaging of suitable metals New Nanobeacons and advances in statistical image reconstruction methods improve coronary fibrin imaging Nanobeacons target fibrin of thrombus on ruptured plaque Fibrin Ca deposit Plaque formation non-separated attenuation from nanoparticle and Ca Selective imaging of nanoparticles
Quantitative Tissue Differentiation Targeted bismuth nanocolloids distinguishes fibrin microdeposits from calcium Pan et. al. Angew Chem Int Ed (2010) Spectral CT image of a fibrin clot phantom with embedded calcium chloride (white arrow) targeted (green arrow) in a glass tube (blue arrows denote wall). Ca-separated Hospitaltour.com Calcium red & Bismuth Gold) Soft tissue invisible due to low X-ray attenuation
Simultaneous Data Acquisition for Perfect Image Registration Pan, Schirra et al., ACS Nano Apr 24;6(4): Ytterbium Nanocolloids for Multicolor CT
Pan, Schirra et al., ACS Nano Apr 24;6(4): PET-Like Hot Spot Imaging with Spectral CT Simultaneous Data Acquisition for Perfect Image Registration
Micro-CT image of a mouse bearing tumor cells that are visualized using Qdot/Ba-nanoparticle-conjugated tumor- targeting antibodies
29 In K-edge subtraction imaging (KES), two simultaneous CT images are acquired using two x-ray beams at two different energies above and below the K-edge of Xe. Absolute quantity of the CA is determined directly on any given point of a lung CT image after subtracting these two images on a logarithmic scale. K-edge subtraction imaging (KES) Xenon Broncheography
The Selective Photon Shield ensures dose neutrality by eliminating spectral overlap. This makes Dual Energy as dose-efficient as any single 120 kV scan. Dual Energy CT During a Dual Source Dual Energy scan, two CT datasets are acquired simultaneously with different kV and mA levels, allowing to visualize differences in the energy-dependence of the attenuation coefficients of different materials. These images are combined and analyzed to visualize information about anatomical and pathological structures.
One Basic Reason for Use of Dual Energy CT: Material Differentiation By scanning a patient at two different energy spectra (e.g. at 56 kV and 76 kV), the attenuation difference of the same material is different. Iodine has higher attenuation difference, compared to bone. Scanning allows the computer to process bone and iodine content on images differently. Routine Use of Dual-energy CT for Material Differentiation Creation of 3D vascular images ("Direct Angio") by easy removal of bony structures Plaque analysis (calcified vs. soft plaques) Lung perfusion Virtual unenhanced scan (creation of unenhanced scan from enhanced images by deleting iodine content from the images) Calculi characterization (uric acid vs. others)
Use the spectral properties of iodine to differentiate it from other dense materials in the dataset (similar to magnetic resonance angiography (MRA)). With Dual Energy CT, it is possible to identify bone by its spectral behavior and to erase it from an angiogram. Then, the iodine in the vessels remains the only dense material in the dataset and a MIP can be calculated from a CT angiogram to closely resemble an MRA. Additionally, it is possible to detect those voxels that contain both calcium and iodine and add them back to the dataset. Calcified plaques of atherosclerotic vessels can thereby be switched on and off in the dataset to visualize both the residual lumen and the plaque distribution. Dual Energy in Angiography
Color Coding of Contrast Material/Virtual Non-Contrast Images The ability to map iodine content in soft tissue organs can be used to study the contrast enhancement of focal lesions, e.g. in the liver or kidney. The CT scan is obtained in normal venous phase. The iodine-related enhancement is color-coded in the image and superimposed with the normal CT image. Additionally, a virtual non-contrast image can be derived from the contrast picture.
Differentiation of Tendons and Ligaments Tendons and ligaments have weak spectral properties, presumably due to the densely packed collagen. It is possible to identify thick tendons and ligaments in Dual Energy CT datasets and to display them separately, for example, to visualize the tendons of the wrist and identify ruptures. However, signal-to-noise ratio is not sufficient to depict thin ligaments; thus the clinical value of this application is limited.