ライフサイエンスコーパス: echo time

1 dial center-out readout (UTE, or "ultrashort echo time").

2 resolved spectroscopy (PRESS) with a 35-msec echo time.

3 z bandwidth, 0.81-kHz amplitude, and 45-msec echo time.

4 s a physical property that is independent of echo time.

5 mages, differences increased with increasing echo time.

6 ry with different image contents at multiple echo times.

7 , and R2* maps calculated by using different echo times.

8 asively from 23Na images obtained with short echo times (0.4 msec) by using external saline solution

9 23)Na signal intensities measured from short echo-time (0.4 msec) (23)Na images to those from an exte

10 ic resonance spectra (repetition time =10 s; echo time =0.35 ms) were acquired every 160 seconds befo

11 al UTE (1.0-mm isotropic spatial resolution; echo time, 0.08 msec) were performed at 3 T.

12 pulse sequence (repetition time, 1.60 msec; echo time, 0.65 msec) and bolus intravenous injection of

13 sional acquisition (repetition time, 4.1 ms; echo times, 0.09/1.09/2.09 ms; field strength, 3 T).

14 gadopentetate dimeglumine and use of a short echo time (1 msec).

15 out of phase (repetition time, 45-180 msec; echo time, 1.4-3.1 msec).

16 GRE sequence (repetition time, 600-750 msec; echo time, 10 msec; in-plane resolution, 196 mm).

17 equence (typically repetition time, 34 msec; echo time, 13 msec; flip angle, 60 degrees ).

18 Quantitative short echo time 1H MRS identified abnormalities in 87% of pati

19 -echo technique (repetition time, 9-12 msec; echo time, 2.1-3.0 msec; flip angle, 30 degrees).

20 ngle shot sequence: repetition time, 5 msec; echo time, 2.3 msec; flip angle, 15 degrees; one coronal

21 oronal acquisition (repetition time, 7 msec; echo time, 2.8 msec; flip angle, 60 degrees) during a si

22 te matter (8 cm3 volume, STEAM sequence with echo time = 20 msec, repetition time = 3.0 seconds) and

23 nce, followed by T2*-weighted gradient-echo (echo time, 25 msec; repetition time, 944 msec) imaging a

24 pulation (replication sample) underwent long echo time (272 msec) proton (hydrogen 1) MR spectroscopy

25 A short echo-time (29 msec) single-voxel (1-cm(3)) proton (hydro

26 resolved spectroscopic (PRESS) localization (echo time 30 ms, repetition time 3000 ms, nominal voxel

27 quence (1.5 T; time to repetition = 2000 ms; echo time = 30 ms; 192 averages).

28 ent 1H-MRSI on a 1.5 T GE Signa scanner [TE (echo time) = 30 ms, TR (repetition time) = 3 s].

29 -echo sequence (repetition time, 3,000 msec; echo time, 30 msec).

30 ubjects underwent structural MRI and a 0.4ms echo time 3D T1-weighted sodium scan as well as the knee

31 magnetic resonance; repetition time: 72 ms; echo time: 45 ms; flip angle: 30 degrees; field of view:

32 e frames in the cardiac cycle, using a short echo time (5 ms) multislice gradient-echo imaging sequen

33 Fast-spiral-sequence (echo time = 5.6-13.8 ms, repetition time = 1 s, 8 interl

34 r imaging (3/1 mm; repetition time, 3000 ms; echo time, 50 ms) were analyzed using second-level rando

35 imaging parameters: repetition time 300 ms, echo time 8 ms, 2-tesla system), followed by triphenylte

36 or FLASH, sequence with short repetition and echo times after intravenous administration of gadopente

37 A spoiled gradient-echo sequence with seven echo times alternately in phase and out of phase was use

38 tients showed increased artifact with longer echo time and higher concentration of injected contrast

39 e water signal at MR imaging with very short echo time and radial center-out readout (UTE, or "ultras

40 on reconstruction technique to achieve short echo times and high signal-to-noise ratio (SNR) efficien

41 length at either large or small scales using echo timing and fringe counting.

42 terogeneity was explained by glioma subtype, echo time, and the proportion of recurrent glioma versus

43 nt-echo pulse sequence, short repetition and echo times, and a rate of three frames per second.

44 weighted imaging, MR imaging with very short echo times, and the availability of some targeted MR ima

45 nts with first-episode psychosis by means of echo time-averaged proton MRS at 4T.

46 ingulate cortex of the subjects by using the echo time-averaged proton MRS technique at 4T (i.e., mod

47 ing the results obtained with the ultrashort-echo-time-based attenuation correction maps currently us

48 mu map (mu mapDX) and a dual-echo ultrashort-echo-time-based mu map (mu mapUTE), which are both calcu

49 QSM was performed for various ranges of echo time by using both the magnitude and phase componen

50 23Na MR imaging with short echo times can be used to quantify absolute tissue sodiu

51 ersion recovery, steady-state, fast gradient-echo time course perfusion, and delayed inversion recove

52 OLD (artifactual) components based on linear echo-time dependence of signals-a characteristic propert

53 A novel dual-echo ultrashort echo time (DUTE) MRI sequence was proposed for head imag

54 nical MR system (repetition time, 11.4 msec; echo time [first echo], 3.7 msec; 18,000 projection angl

55 reported attempts with dual-echo ultrashort echo time, for which the Jaccard distance was in the 47%

56 Ultrashort echo-time free-breathing MRI acquisitions were performed

57 eins in the brain, a three-dimensional, long echo time, gradient-echo sequence that depended on the p

58 l or fast spin-echo and gradient-echo (GRE) (echo time > or = 6.0 msec) imaging were identified.

59 py studies at higher fields and with shorter echo time have revealed abnormalities in glutamate and g

60 Chemical-shift images with six widely spaced echo times (in 3.5-msec increments) were acquired to cor

61 Short echo time localized proton magnetic resonance spectrosco

62 ere examined with a hybrid radial ultrashort echo time magnetic resonance (MR) imaging sequence at 3.

63 lgorithm was based on a dual-echo ultrashort-echo-time MR imaging sequence to calculate the R2 map, f

64 Localized single-voxel, 20-msec-echo-time MR spectra (including N-acetylaspartate [NAA],

65 Short-echo-time MRS was used to measure N-Acetyl-aspartate (NA

66 locity-encoding value) (repetition time msec/echo time msec = 16/9).

67 e Look-Locker approach (repetition time msec/echo time msec, 1,000/3.5; flip angle, 10 degrees ).

68 T2 weighted (repetition time msec/effective echo time msec, 1,800-3,000/30-102).

69 lanar imaging sequence (repetition time msec/echo time msec, 10 123/40; b=1200 sec/mm2).

70 (23)Na (repetition time msec/echo time msec, 160/0.35) and (35)Cl (40/0.6) MR imaging

71 weighted gradient-echo (repetition time msec/echo time msec, 180/2.3; transmission angle, 55 degrees

72 DC maps were generated (repetition time msec/echo time msec, 2000/67; section thickness, 4 mm; in-pla

73 suspended respiration (repetition time msec/echo time msec, 3.2/1.6; section thickness, 5 mm; in-pla

74 le-shot fast spin-echo (repetition time msec/echo time msec, 4,500/940) imaging was performed in the

75 ole-heart acquisitions (repetition time msec/echo time msec, 4/1.35; 20 degrees flip angle; 1 x 1 x 2

76 orthogonal planes, with repetition time msec/echo time msec, 5-12/62-95; number of signals acquired,

77 -dimensional MR images (repetition time msec/echo time msec, 8.86/4.51; flip angle, 25 degrees ) acqu

78 gradient-echo sequence (repetition time msec/echo time msec, 800/1.8-49.8) was performed at embryonic

79 resonance (MR) imaging (repetition time msec/echo time msec/inversion time msec [fixed], 5.2/2.5/430;

80 ging (first and second repetition times msec/echo time msec: 72, 192/2.2; transmission angle: 60 degr

81 t suppression (4.2/1.8 [repetition time msec/echo time msec], 12 degrees flip angle), was performed i

82 tions (3.6-4.5/1.5-1.9 [repetition time msec/echo time msec], 12 degrees flip angle).

83 uence (3.4-6.8/1.2-2.3 [repetition time msec/echo time msec], 25 degrees -40 degrees flip angle).

84 aging (3.8-4.2/1.3-1.7 [repetition time msec/echo time msec], 25 degrees-40 degrees flip angle) was p

85 2 x 352 matrix, 58/2.0 [repetition time msec/echo time msec], 30 degrees flip angle, 15.6-kHz bandwid

86 echo sequence (3.4/1.2 [repetition time msec/echo time msec], 45 degrees flip angle, and six to eight

87 -echo imaging (4.2/1.8 [repetition time msec/echo time msec]; flip angle, 12 degrees; interpolation i

88 cho spin-echo sequence (repetition time msec/echo times msec, 1500/24, 36, 48, 60, 72, 84, 96, 108, 1

89 ort echo time sequence (repetition time msec/echo times msec, 30/0.075, 2, 5, 12, 18).

90 ady-state precession (repetition time [msec]/echo time [msec] = 5.0/2.0, with 50 degrees flip angle)

91 top NMR system using a CPMG sequence with an echo time of 1.25 ms providing the ability to detect sig

92 x 220 microns, slice thickness of 1 mm, and echo time of 16 ms.

93 alize, with a relaxation time of 3000 ms and echo time of 30 ms.

94 negative TLE patients underwent 1H MRS at an echo time of 30 msec on a 1.5-T GE Signa scanner.

95 Spectra obtained with an echo time of 31 msec showed resonances from water and mo

96 quence with a repetition time of 18 msec, an echo time of 5 msec, and a flip angle of 10 degrees show

97 d-echo sequence with the shortest attainable echo time of approximately 4 msec (T2* mapping).

98 uence with a repetition time of 550 msec and echo times of 12.8, 19.8, and 26.8 msec.

99 increase in glutamate was similar when using echo times of 30 and 144 ms, indicating that exercise-re

100 eady state, or GRASS, sequence was used with echo times of 4-40 msec at 4-msec increments.

101 ose of metabolic quantification at 3.0 T and echo times of less than 100 msec, an average T2 value pe

102 Ultrashort-echo-time or zero-echo-time (ZTE) pulse sequences can ca

103 ith QSM did not show significant change over echo time (P = .31), and the variation was significantly

104 A short echo time Point RESolved Spectroscopy (PRESS) spectrosco

105 n age, 25 years) by using single-voxel short-echo-time point-resolved 1H MR spectroscopy.

106 and single-voxel MR spectroscopy with a long-echo-time point-resolved technique.

107 tion by using a three-dimensional very short echo time sequence (repetition time msec/echo times msec

108 n, liver, and kidney and a radial very-short-echo time sequence for lung imaging.

109 and T2* maps were acquired with the variable echo-time sequence and the GAG CEST values were acquired

110 We conducted a short echo time, single-voxel, in vivo proton spectroscopy stu

111 ied point resolved spectroscopy sequence: 24 echo time steps with 20-ms increments).

112 Water-suppressed, long echo time, stimulated-echo hydrogen-1 chemical shift ima

113 ge-bone specimens at 3 T by using ultrashort echo time (TE) (UTE) and conventional pulse sequences to

114 meters were number of excitations (NEX) = 1, echo time (TE) = 14 msec, recovery time (TR) = 2 sec, ec

115 Here, we investigated the use of long-echo time (TE) proton magnetic resonance spectroscopy (1

116 ion (MEDIC), T2-weighted GRE with an 11-msec echo time (TE), and T2-weighted GRE with a 15-msec TE.

117 rformed at short (< 45 ms) or long (> 45 ms) echo time (TE), each with particular advantages.

118 ighted conventional SE (repetition time msec/echo time [TE] msec = 3,100/ 80,160) and fast SE (5,000-

119 d fast spin-echo (FSE) (repetition time msec/echo time [TE] msec, 4,000/13), sagittal T2-weighted FSE

120 trospectively evaluated gradient-echo (GRE) (echo time [TE], > or = 9 and 4-5 msec) and turbo short i

121 ed: gradient-echo (GRE) echo-planar imaging (echo time [TE], 30 msec; flip angle, 90 degrees ; n = 10

122 resonance (MR) images obtained at different echo times (TEs).

123 quisition with echo shifting, which leads to echo times that are longer than the repetition time.

124 iple spin-echo (SE) technique with different echo times to measure T1 and T2, respectively.

125 n time (to suppress T1 effects) and multiple echo times (to estimate T2 effects); the reference fat f

126 angle (to suppress T1 effects) and multiple echo times (to estimate T2* effects); imaging FF was cal

127 follows: for proton density, repetition time/echo time (TR/TE) 2300/5.6; for T2, TR/TE 2300/62; and f

128 hydrogen-1 chemical shift imaging and short echo time unsuppressed chemical shift imaging were perfo

129 ased numeric approach with use of ultrashort echo time (UTE) magnetic resonance (MR) imaging in vivo

130 red using the standard DIXON- and ultrashort echo time (UTE)-based approaches.

131 generate whole-head mu maps from ultrashort echo-time (UTE) MR imaging sequences.

132 Ultrashort-echo-time (UTE) sequences have been proposed in the past

133 Ultrashort-echo-time (UTE) sequences have been used to separate cor

134 Optimal effective echo time was 50 msec.

135 When echo time was increased from approximately 20 to 40 msec

136 In three subjects, echo time was varied to determine the glycogen and choli

137 A series of T2-weighted pulses with 16 echo times was used to enable precise T2 mapping and cal

138 nal radial gradient-echo sequence with short echo time, we performed sodium magnetic resonance imagin

139 MR elastographic pulse sequences with short echo times were compared with those obtained with the co

140 GRE sequences with short repetition and echo times were more accurate and precise than spin-echo

141 attenuated (median 45% decrease) when longer echo times were used for venous suppression, but it did

142 ts between computed tomography (CT) and zero echo time (ZTE) magnetic resonance (MR) imaging of the s

143 Ultrashort-echo-time or zero-echo-time (ZTE) pulse sequences can capture bone informa

144 n brain PET/MRI, the major challenge of zero-echo-time (ZTE)-based attenuation correction (ZTAC) is t

145 a novel, recently published method for zero-echo-time (ZTE)-based MR bone depiction and segmentation