ライフサイエンスコーパス: Dixon

1 Dixon analysis shows that epostane inhibits the 3beta-HS

2 Dixon analysis with GMP yielded a signature plot for com

3 Dixon et al. accurately describe subtle mechanisms of di

4 Dixon et al. have highlighted the importance of a politi

5 Dixon et al. overlook the fact that contact predicts not

6 Dixon et al. suggest that the psychological literature o

7 Dixon fat and water MR images were registered to CT imag

8 Dixon fat-water separation MR images were manually segme

9 Dixon images detected 15 of 47 lung lesions whereas VIBE

10 Dixon plots show that inhibition is competitive for the

11 Dixon was among the founders of modern immunology and a

12 Dixon water-fat distribution was not significantly diffe

13 Dixon's up-and-down sequential method was used to determ

14 18)F-FDG PET data were acquired along with 2 Dixon MR-AC maps for each examination.

15 hat maps between the four 2-dimensional (2D) Dixon MR images (water, fat, in-phase, and out-of-phase)

16 Although a Dixon plot of the inhibition of IKK-2 by BMS-345541 show

17 a regular 4-compartment segmentation from a Dixon sequence ("Dixon").

18 thyl cations has been quantified by use of a Dixon plot, yielding K = 1.1(3) x 10(-4) M, 4.7(5) x 10(

19 performed by segmentation methods based on a Dixon MR sequence providing up to 4 different tissue cla

20 nt overnight polysomnography and MRI using a Dixon sequence.

21 PET data were reconstructed using a Dixon-based mu map (mu mapDX) and a dual-echo ultrashort

22 ing-based method from CAIPIRINHA-accelerated Dixon images were more accurate than those generated wit

23 ing-based method from CAIPIRINHA-accelerated Dixon images were more accurate than those generated wit

24 ment air pockets from CAIPIRINHA-accelerated Dixon images, with accuracy comparable to that of semiau

25 dard Dixon 4-compartment segmentation alone, Dixon with a superimposed model-based bone compartment,

26 perimposed model-based bone compartment, and Dixon with a superimposed bone compartment and linear AC

27 formed using low-dose CT data for PET/CT and Dixon MRI sequences for PET/MR.

28 T(1rho) MR imaging and Dixon water-fat MR imaging of the affected upper arms we

29 cated linear, noncompetitive inhibition, and Dixon plot analysis from competition studies with a zinc

30 ual inspection of the thoracic MR-AC map and Dixon images from which it is derived remains crucial fo

31 parison of MAPE between the PASSR method and Dixon segmentation, CT segmentation, and population aver

32 ective 3D turbo spin echo for (31)P-MRI, and Dixon multi-echo GRE for fat-water imaging on a 3 T clin

33 -weighted, short-tau inversion-recovery, and Dixon-type sequences.

34 ilters, statistics for weighted samples, and Dixon's test for outliers, to evaluate protein abundance

35 The t-test and Dixon's Q-test were applied in order to examine statisti

36 r the VIBE sequence (P < 0.0001 for VIBE and Dixon sequence).

37 learning model: we call this method ZTE and Dixon deep pseudo-CT (ZeDD CT).

38 ral network was trained to transform ZTE and Dixon MR images into pseudo-CT images.

39 ntator on 1200 manually annotated UK Biobank Dixon MRI sequences (50 participants), 221 in-house abdo

40 Separate indexes defined by Dixon (7 food groups, saturated fat, and alcohol), Melle

41 by Brij-35 was a mixed type as determined by Dixon's plot; however, the inhibition mechanism of endom

42 ment the psychological approach put forth by Dixon et al., but with minimal ancillary assumptions.

43 o solve the resulting problems identified by Dixon et al., we suggest analyzing the psychological pro

44 by Hanes analysis and 0.6 and 0.4 microM by Dixon analysis.

45 The analysis offered by Dixon et al. fails to acknowledge that the attitudes tha

46 The early studies by Dixon and his group examining the models of acute or chr

47 us sorbinil-supplemented medium suggested by Dixon plot that neither galactitol nor galactose interac

48 hod for whole-body PET/MR imaging, combining Dixon-based soft-tissue segmentation and model-based bon

49 significantly lower image quality comparing Dixon and VIBE sequence with CT whereas PET from PET/CT

50 Conclusion Dixon T2-weighted fat-only and water-only imaging provid

51 ontrast, ellagic acid produced a curvilinear Dixon plot suggesting partial inhibition of nucleotide a

52 We describe Dixon-VIBE Deep Learning (DIVIDE), a deep-learning netwo

53 se a fat and water map derived from a 2-echo Dixon MRI sequence in which bone is neglected.

54 the use of a novel free-breathing multi-echo Dixon technique for quantitative myocardial perfusion.

55 ce (MR) imaging protocol (sagittal spin-echo Dixon T2-weighted fat-only and water-only imaging) would

56 sagittal spin-echo T1-weighted and spin-echo Dixon T2-weighted water-only imaging).

57 were assessed with a chemical shift-encoded Dixon sequence and multiecho spin-echo sequence.

58 metric interpolated breath-hold examination (Dixon-VIBE) images currently acquired for AC in some com

59 metric interpolated breath-hold examination) Dixon for attenuation correction and contrast-enhanced V

60 relation was observed between FF(MRF) and FF(Dixon) (R(2) = 0.97, P < .001).

61 red with the three-point Dixon technique (FF(Dixon)), water T2 mapping, and MRF T1-FF, from which the

62 lowest quintiles for all indexes as follows: Dixon (HR: 0.77; 95% CI: 0.69, 0.87), Mellen (HR: 0.78;

63 e lesions, the biases were 5.1% +/- 5.1% for Dixon and 5.2% +/- 5.2% for Model.

64 y a factor of 4 for bone lesions (10.24% for Dixon PET and 2.68% for ZeDD PET) and by a factor of 1.5

65 or of 1.5 for soft-tissue lesions (6.24% for Dixon PET and 4.07% for ZeDD PET).

66 rest was 2.4% +/- 2.5% and 2.7% +/- 2.7% for Dixon and Model, respectively, compared with CT-based AC

67 on was -7.4% +/- 5.3% and -2.9% +/- 5.8% for Dixon and Model, respectively.

68 g for bone detection and gradient echoes for Dixon water-fat separation in a radial 3-dimensional acq

69 n Enders at Harvard, who pointed me to Frank Dixon at Scripps in La Jolla, California, for postdoctor

70 Under Frank Dixon, my work examined how antibodies to the glomerular

71 VD than the textural features extracted from Dixon sequences and FDG PET.

72 mated measurements of fat fraction (FF) from Dixon images.

73 segmented separately, 14 muscles total) from Dixon MRI scans (n = 17, 17 scans < 2 weeks post motor v

74 s of affinity that correlated with the ideal Dixon-Webb competitive profile.

75 Three points that are implicit in Dixon et al.'s paradigm-challenging paper serve to make

76 scussing my work in Israel (now mentioned in Dixon et al.'s note 6) on the processes and practices th

77 competitive inhibitor of MgATP with a linear Dixon plot.

78 This multiecho TSE modified Dixon (mDixon) sequence was optimized by using simulatio

79 is study to implement an algorithm modifying Dixon-based MR imaging datasets for attenuation correcti

80 sing 3-dimensional CAIPIRINHA-accelerated MR Dixon datasets from 35 subjects and was evaluated agains

81 udo-CT images from CAIPIRINHA-accelerated MR Dixon images.

82 he attenuation map was obtained using the MR Dixon method currently available on the Siemens Biograph

83 rove (18)F FDG PET image quality by using MR Dixon fat-constrained images to constrain PET image reco

84 by using a commercially available multipoint Dixon pulse sequence with a 1.5-T MRI system.

85 A single-breath-hold multipoint Dixon-based acquisition was performed with commercially

86 pleural effusions through use of multipoint Dixon fat quantification.

87 In ex vivo studies, multipoint Dixon-derived fat fraction was higher in chylous versus

88 with hepatic MR imaging by using multipoint Dixon techniques is highly reproducible across readers,

89 urpose To assess whether MRI with multipoint Dixon fat quantification allows for noninvasive differen

90 unther (HR: 0.84; 95% CI: 0.73.0.97) but not Dixon (HR: 1.01; 95% CI: 0.80, 1.28).

91 n-based mu maps using the MAVRIC in areas of Dixon signal voids.

92 A key argument of Dixon et al. in the target article is that prejudice red

93 duced the whole-brain SUV estimation bias of Dixon-based PET/MR AC by 95% compared with reference CT

94 t-specific multiparametric MRI consisting of Dixon MRI and proton-density-weighted ZTE MRI to directl

95 in immunopathology and also cover facets of Dixon's overall contributions to immunology.

96 Purpose To test the potential of Dixon T2-weighted fat-only sequences to replace T1-weigh

97 nd even allowing retrospective processing of Dixon-VIBE data.

98 This commentary focuses on Dixon et al.'s discussion on the dangers of employing pr

99 ce standard (short-tau inversion recovery or Dixon) techniques.

100 erage of differences between PET(CT) and PET(Dixon) (mean PET(CT)-PET(Dixon) SUV, 0.0006; PET(CT)-PET

101 PET(CT)-PET(Dixon) SUV, 0.0006; PET(CT)-PET(Dixon) SD, 0.0264; 95% confidence interval, [-0.0510,0.0

102 een PET(CT) and PET(Dixon) (mean PET(CT)-PET(Dixon) SUV, 0.0006; PET(CT)-PET(Dixon) SD, 0.0264; 95% c

103 obtained after AC using the Dixon-VIBE (PET(Dixon)), DIVIDE (PET(DIVIDE)), and CT-based (PET(CT)) me

104 tely followed by PET/MR imaging with 2-point Dixon attenuation correction.

105 The MRI consisted of 2-point Dixon imaging for attenuation correction, standard seque

106 te Free Precession and T(1)-weighted 2-point Dixon sequences covering the entire fetus.

107 PET/MR imaging included a 2-point Dixon water-fat separation method.

108 ue decomposition is achieved using a 3-point Dixon-like decomposition.

109 Proton MR spectroscopy (MRS) and 8-point Dixon MR imaging (MRI) measured muscle fat fraction (FF)

110 ast spin-echo, or water-specific three-point Dixon gradient-echo) was alternated with freehand manipu

111 Water-specific three-point Dixon images are successful in regions of B0 heterogenei

112 Three-point Dixon images were superior to extended two-point Dixon a

113 Three-point Dixon imaging provides a robust method for creating fat-

114 on comprised FF mapping with the three-point Dixon method, water T2 mapping, and water T1 mapping bef

115 A three-point Dixon reconstruction algorithm was used to generate wate

116 aration was performed by using a three-point Dixon reconstruction from in- and opposed-phase black-bl

117 ping of the FF measured with the three-point Dixon technique (FF(Dixon)), water T2 mapping, and MRF T

118 n images were superior to extended two-point Dixon and fat-suppressed images and to images generated

119 t-fraction (SFF) analysis based on a 2-point-Dixon water-fat separation method in whole-body simultan

120 The three-point-Dixon fat water separation technique was used to determi

121 The proposed Dixon motion correction technique was compared to the st

122 R short inversion time inversion-recovery ), Dixon-type liver accelerated volume acquisition ( LAVA l

123 construction is improved over segmentation- (Dixon and Siemens UTE) and registration-based methods, e

124 ing low-dose CT for the PET/CT and segmented Dixon MR imaging data for the PET/MR.

125 d a constraint based on fat/water-separating Dixon MR images that shift activity away from regions of

126 y 3-dimensional dual gradient-echo sequence (Dixon) used for MR imaging-based PET attenuation correct

127 artment segmentation from a Dixon sequence ("Dixon").

128 f-phase echoes, required for chemical shift (Dixon) reconstruction, in the same repetition by using p

129 g the original CT, our synthetic CT, Siemens Dixon-based mu maps, Siemens UTE-based mu maps, and defo

130 29.767, 29.34, and 27.43 dB for the Siemens Dixon-, UTE-, and registration-based mu maps.

131 R AC methods were compared with CT: standard Dixon 4-compartment segmentation alone, Dixon with a sup

132 hesize a pelvis pseudo-CT scan from standard Dixon-VIBE images, allowing for accurate AC in combined

133 a novel AC method that supplements standard Dixon-based tissue segmentation with a superimposed mode

134 is pseudo-CT maps based only on the standard Dixon volumetric interpolated breath-hold examination (D

135 s to assess the reproducibility of standard, Dixon-based attenuation correction (MR-AC) in PET/MR ima

136 I argue that Dixon et al. fail to maintain a careful distinction betw

137 Here, I argue that Dixon et al. have overstated the prevalence of "benevole

138 The Dixon fat images, unaffected by the dynamic contrast-enh

139 The Dixon magnetic resonance imaging technique was used to q

140 The Dixon MRI sequences acquired for attenuation correction

141 The Dixon-based method performed substantially worse (the me

142 The Dixon-based method performed substantially worse, with a

143 d to separate cortical bone and air, and the Dixon technique has enabled differentiation between soft

144 the gold standard CT-based approach and the Dixon-based method available on the Biograph mMR scanner

145 sing the reference CT-based approach and the Dixon-based method.

146 An algorithm was implemented correcting the Dixon-based mu maps using the MAVRIC in areas of Dixon s

147 er, with a detection rate of 9 of 33 for the Dixon sequence and 15 of 33 for the VIBE sequence (P < 0

148 ned to synthesize pseudo-CT mu-maps from the Dixon images.

149 ined to synthesize pseudo-CT u-maps from the Dixon images.

150 ed 4D MRI volume and the AM derived from the Dixon MR image to generate respiration-synchronized MR i

151 MRI of the lower extremities included the Dixon sequence, multicomponent T2 mapping, and DTI calcu

152 imes smaller than the relative change of the Dixon method.

153 llocation of PET/MR findings by means of the Dixon MRI sequence was comparable to allocation of PET/C

154 PASSR outperformed the Dixon, CT segmentation, and mean atlas methods by reduci

155 ter, which were significantly lower than the Dixon, CT segmentation, and mean atlas values (P < .01).

156 8%, which was significantly smaller than the Dixon- (100%) and CT- (39%) derived values.

157 re assessed via water-fat contrast using the Dixon method and via water-saturation efficiency using f

158 second non-linear correction step using the Dixon water images to remove residual motion.

159 e SUVs (in g/mL) obtained after AC using the Dixon-VIBE (PET(Dixon)), DIVIDE (PET(DIVIDE)), and CT-ba

160 use of the lack of bone information with the Dixon-based MR sequence, bone is currently considered as

161 Three Dixon-based MR AC methods were compared with CT: standar

162 Thanks to Dixon's up-and-down method we proved that with the induc

163 dy involving seventy subjects that underwent Dixon MRI of the pelvis.

164 al Consortium grant; Northwestern University Dixon Translational Science Award; Simpson Querrey Lung

165 was examined for both Ag(+) and Cu(2+) using Dixon and Cornish-Bowden plots, where a strong correlati

166 enohumeral models by transfer learning using Dixon-based sequences.

167 57 +/- 0.54, P = 0.0001) or T1-weighted VIBE Dixon MRI (2.57 +/- 0.54, P = 0.0002).

168 h PET [from PET/CT; set A], T1-weighted VIBE Dixon with PET [set B], and T1-weighted TSE with PET [bo

169 interpolated breath-hold examination (VIBE) Dixon sequence for attenuation correction and an unenhan

170 Training by and association with Dixon and his other postdoctoral fellows, my independent

171 with deep MRAC (-0.7% +/- 1.1) compared with Dixon-based soft-tissue and air segmentation (-5.8% +/-

172 We disagree with Dixon et al. by maintaining that prejudice is primarily

173 r fat-suppression inhomogeneity indexes with Dixon (1.0%) and SHARP (2.4%) compared with CHESS (10.7%

174 In line with Dixon et al.'s argument, I contend that prejudice should

175 25.5% +/- 7.9% underestimation observed with Dixon was reduced to -4.9% +/- 6.7% with Model.

176 nd muscular fat fraction was quantified with Dixon-type imaging.

177 T1-weighted 3-dimensional MRI sequence with Dixon-based fat and water separation was also acquired a