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1 ve realistic Hounsfield units in the patient phantom.
2 the use of the ACR mammography accreditation phantom.
3 igation of a multi-branched vascular network phantom.
4 of the abdomen and thigh with a calibration phantom.
5 Manufacturers Association 2007 image-quality phantom.
6 ated with the mammographic accreditation ACR phantom.
7 t of detection was assessed in a B16F10 cell phantom.
8 of the systems were estimated by using a CT phantom.
9 on combinations at fixed exposure for either phantom.
10 smaller exposure reduction than in the 30-cm phantom.
11 sing an edge pattern and a thin-line optical phantom.
12 branch vessels in a cryogel abdominal aortic phantom.
13 struction was also assessed using a Jaszczak phantom.
14 i-detector row CT scanner with a calibration phantom.
15 robubble concentration in a tissue mimicking phantom.
16 ietary algorithm was assessed by using a hip phantom.
17 ecause this study only evaluated images of a phantom.
18 anteroposterior vessels at 3 T in a vascular phantom.
19 lication of SSPiM OCTA signal in an in vitro phantom.
20 pression and cells in a 3D engineered tissue phantom.
21 eart wall insert of an anthropomorphic torso phantom.
22 by utilizing a boneless chicken breast as a phantom.
23 rovided the most accurate results in a large phantom.
24 L4 vertebral body with use of a calibration phantom.
25 s (TLD) placed inside a CIRS anthropomorphic phantom.
26 rved between the sphere and the renal cortex phantoms.
27 stortion values and distributions in virtual phantoms.
28 2.0 to assess the dose using new voxel-based phantoms.
29 sed technique was validated by using agarose phantoms.
30 ell as new cases using realistic voxel-based phantoms.
31 sceptometry has been demonstrated with liver phantoms.
32 ues and with basic geometric anthropomorphic phantoms.
33 er than the doses derived from old geometric phantoms.
34 image uniformity and noise by using uniform phantoms.
35 th OLINDA/EXM software using adult reference phantoms.
36 ing thin capillary and water-filled Jaszczak phantoms.
37 , 16.6, and 10.8 for the 30-, 35-, and 45-cm phantoms.
38 distribution volume, using tissue-simulating phantoms.
39 NDA/EXM 1.2 for the standard male and female phantoms.
40 agents and calcium phosphate were imaged in phantoms.
41 nto 58 extended cardiac-torso (XCAT) patient phantoms.
42 ion of anthropomorphic voxel-based pregnancy phantoms.
43 standard acrylamide phantoms vs macroporous phantoms (10kPa), improving the correlation to the burst
48 esected human brain cancer and from a silica phantom acquired by a 1310 nm swept-source OCT (SS-OCT)
54 ed against sonomicrometry in a dynamic heart phantom and among each other in 136 patients included pr
56 1) (with the greatest reduction in the 40-cm phantom and at lower exposures) and improved lesion CNR
59 it is feasible to acquire PCSI spectra in a phantom and in humans and that PCSI provides an efficien
60 l demonstration is conducted in a calibrated phantom and in vivo in the brain of two healthy voluntee
63 o the abdomen phantom, linear correlation of phantom and patient Hounsfield units was confirmed (r =
64 ithm (termed Q.Clear) was investigated using phantom and patient scans to optimize the reconstruction
69 ncidence counting rate from the (18)F-filled phantom and the (22)Na point source on all 3 systems.
70 ging system was tested with tissue-mimicking phantoms and an ex vivo chicken liver through 2D/3D imag
77 ity to small-molecule dyes was determined in phantoms and in vivo; precision was assessed in vivo usi
80 s placed into 30-, 35-, and 45-cm-wide water phantoms and scanned with a dual-source CT scanner in bo
81 SPECT/CT imaging, a set of kidney dosimetry phantoms and their spherical counterparts was designed a
82 ted emission spectrum (0.014-0.041 mug/ml in phantoms), and (III) optical-property corrected PpIX est
83 and dead cells was next evaluated using MRI phantoms, and in vivo using both immune-competent and im
86 ted with realistic voxelwise anthropomorphic phantoms are higher than the doses derived from old geom
89 ise-equivalent count rate from a mouse-sized phantom at 3.7 MBq was 11.1 kcps and peaked at 20.8 kcps
94 ation liver lesions in a semianthropomorphic phantom by using either a discrete circuit (DC) detector
95 ic iodine-based contrast material in a colon phantom by using the characteristic k edge of gadolinium
100 oncentration were well correlated with known phantom concentrations (R(2) = 1.00, P < .001) over a br
102 ere SPIO compositions was determined from 32 phantoms constructed with agarose gel and in eight conce
103 Materials and Methods A large elliptical phantom containing iodine (2, 5, and 15 mg/mL), simulate
104 ation of gold and iodine concentrations in a phantom containing mixtures of the contrast agents.
110 er variability over this large collection of phantom data gives, for the first time, estimates of rec
113 past 5 y has generated a rich, well-curated phantom dataset from which PET/CT make-and-model and rec
114 the CTN has collected 406 well-characterized phantom datasets from 237 scanners at 170 imaging sites
116 f voxel-based, realistic human computational phantoms developed by the RADAR committee of the Society
117 image quality indicators for the CATPHAN 600 phantom; - dosimetric indicators of exposure (DLP i CTDI
121 e image quality metrics were compared in the phantom experiment by using multiple linear regression a
124 This has been demonstrated quantitatively in phantom experiments as well as in patient imaging, for w
125 When compared with standard PET images, the phantom experiments showed a bias reduction of 14% in ac
128 Performance was evaluated using simulations, phantom experiments, and clinical repeatability studies.
132 and phantoms filled with (18)F, as well as a phantom filled with either (99m)Tc or (177)Lu, we evalua
135 work can realize realistic and customizable phantoms for diagnostic and therapeutic radiology, inclu
136 material into computational anthropomorphic phantoms for estimation of organ dose at computed tomogr
137 y 3D printed CH structures, from soft tissue phantoms for surgical training and simulations to mechan
138 y, which is a phenomenon that we refer to as phantom fullness, may be useful in lowering energy intak
151 s were performed by using a tissue-mimicking phantom in multiple oxygenation conditions (n = 6) to co
152 manufacturing individualized anthropomorphic phantoms in many clinical applications in nuclear medici
153 ablished which could be carried out with the phantom, including: depth of penetration, dead zone, dis
154 sites were requested to submit a variety of phantoms, including uniform and American College of Radi
155 lgorithm was tested and validated on virtual phantoms incorporating known degrees and distributions o
156 mance of our capsule, we imaged fluorescence phantoms incorporating principal tissue fluorophores (fl
159 cation module to monitor saliva glucose in a phantom jaw imitating the structure of the human oral ca
160 College of Radiology (ACR) CT accreditation phantom LCR section at volume CT dose indexes of 8, 12,
162 Amputees who wish to rid themselves of a phantom limb must weaken the neural representation of th
165 results may have important implications for phantom-limb pain and complex regional pain syndrome.
166 rection procedure was applied to the abdomen phantom, linear correlation of phantom and patient Houns
167 es where the fly turned and the tongue hit a phantom location consistent with the fly's earlier traje
168 proposed imaging technique was validated in phantom measurements and then used for cardiac T1 mappin
174 s work has demonstrated feasibility in solid phantoms, measurements in blood have proved significantl
175 omic force and confocal microscopy, we image phantom microstructures with nanoscale resolution, and a
176 n handling cytosolic metals in larvae of the phantom midge (Chaoborus) collected from five mining-imp
180 erican College of Radiology CT accreditation phantom (module 2, low contrast) were performed for mult
182 For this purpose, 3-dimensional (3D)-printed phantoms of different geometries were manufactured, diff
183 o develop a method to create anthropomorphic phantoms of individual patients with high precision of a
184 ve the dose with the classic anthropomorphic phantoms of pregnant women, then into OLINDA/EXM 2.0 to
187 dy aimed to create acrylamide-based hydrogel phantoms of varying porosity and stiffness, which we hyp
188 surements for imaging through a 15 mm tissue phantom, our method shows a two fold improvement in spat
190 aptive plasticity theory, according to which phantom pain arises from remapping of cortically neighbo
192 m and American College of Radiology-approved phantoms, PET/CT images, and examples of clinical images
194 ge noise was evaluated for a range of radial phantom positions, iteration numbers, and postreconstruc
195 ues derived from several voxel computational phantoms previously developed at Helmholtz Zentrum Munch
198 e]) exposure reduction for the 30- and 40-cm phantoms, respectively (adjusted P < .001 and .04 respec
199 muSv/MBq in reference human male and female phantoms, respectively), and the effective dose equivale
200 m and American College of Radiology-approved phantom results between scanner manufacturers were simil
204 Direct microscopic observation of these phantoms, revealed a significant (p = 0.0024) correspond
210 tionship between cortical reorganization and phantom sensations or pain either with this measurement
211 was also examined to assess the influence of phantom shape and size on the calibration constants.
214 placed into a 36-cm-wide torso-shaped water phantom simulating the abdomen of a medium-sized patient
219 s, but it is unclear how these relate to the phantom sound itself, as opposed to predisposing factors
220 siform cells suggests that a neural code for phantom sounds emerges in this brainstem location and li
223 interconnectivity decreased with increasing phantom stiffness and better mimicked the microstructure
235 pe PC collimator was used in an experimental phantom study to assess and compare contrast recovery co
237 were used in the clinical evaluation, and a phantom study using an anatomic brain phantom was conduc
243 priate optimization and validation, hydrogel phantoms such as the one investigated here could be used
244 computed tomographic (CT) quantitation in a phantom system comparing fast kilovolt peak-switching, d
245 antified in the soleus muscle by using three phantoms that contained 10-, 20-, and 30-mmol/L NaCl sol
252 ns from normal iron dose (0.05 mg Fe/g liver phantom) to 5 mg Fe/g liver phantom iron overload (100X
256 aracterization of tissues and fabrication of phantoms used for diagnostic and therapeutic purposes ov
259 -volume effects were observed for decreasing phantom volumes (percentage difference of up to 9.8% for
261 and show that angular momentum is hidden in phantom vortices modes which so far seem to have evaded
262 from 31% to 43% when in standard acrylamide phantoms vs macroporous phantoms (10kPa), improving the
264 atient, a patient-specific digital perfusion phantom was constructed to simulate the same protocol at
267 Materials and Methods A custom-made colon phantom was filled with nonionic iodine-based contrast m
270 ies were performed: an (18)F-filled Jaszczak phantom was measured, and the impact of including PSF mo
271 erican College of Radiology CT accreditation phantom was scanned by using a dual-source multidetector
272 ical Manufacturers Association image-quality phantom was scanned on a time-of-flight PET/CT scanner a
273 Materials and Methods An anthropomorphic phantom was scanned with 192-section CT without and with
275 red with a (68)Ge line source in the scatter phantom was stable within the range of 40.4%-40.6%.
282 recovery coefficients for the image-quality phantom were 53.7, 64.0, 73.1, 82.7, 86.8, and 90.7 for
283 ameter of supra-slice objects in the Catphan phantom were taken into consideration.Both iterative alg
284 ation curves from an ex vivo experiment in a phantom were used to design CM protocols for CT angiogra
285 ctive doses for the standard male and female phantoms were 0.013 +/- 0.004 and 0.014 +/- 0.004 mSv/MB
286 efficients (0-10 cm(-1)) in hemoglobin-based phantoms were approximately 2% and 6%, respectively.
289 e greatest impact on signal repeatability in phantoms were rotational position and user experience, b
291 ound to be dependent on the stiffness of the phantoms, while drug release was found to be dependent o
294 rlo simulation was run using a modified XCAT phantom with additional and edited cerebrospinal fluid (
295 es of 3-T MR imaging were measured in a head phantom with no grid, a conventional grid, and a PTFOS g
297 nits were investigated by printing geometric phantoms with gray scales ranging from 0% (white) to 100
298 Materials and Methods An anthropomorphic phantom without or with a 5-cm-thick fat-mimicking ring
299 ication (VIDA) and 4D Extended Cardiac Torso Phantom (XCAT) were extended to provide radiation safety
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