ライフサイエンスコーパス: raster

1 d 45 degrees fundus images and two undilated raster 3D-OCT scans (512 x 128) covering the macula and

2 nderwent digital FA and 512 x 128 horizontal raster 3D-OCT scans on the same day in a retina subspeci

3 images of the pore openings were obtained by rastering a glass-sealed conically shaped Pt tip (approx

4 eration of laser beam parameters (spot size, rastering across the sample surface) and actual sample c

5 In this method, a large diameter laser beam rasters across the surface of a partly aligned CNT texti

6 ack, and South Asian origin underwent SD OCT raster and enhanced depth imaging scan.

7 SERAPHIM ("Studying Environmental Rasters and PHylogenetically Informed Movements") is a s

8 Circular, raster, and radial scans of left eye optic nerves were a

9 ed methodologies (spot ablation, single line raster, and two-dimensional imaging) were also used to d

10 uniquely suited to scan times typical of the raster approach that is ubiquitous in TPLSMlaboratories.

11 al from various surface locations on a 4 x 4 raster array (50 mum pitch distance, ablation crater dia

12 The raster assembly can also improve throughput as foils con

13 The raster assembly provided a 5.7 fold increase in the surf

14 In contrast to raster assembly that assigns optical tweezers to each pa

15 n is statistically comparable to the 25-line raster at detecting fluid in DME, BRVO/CRVO, and central

16 serous chorioretinopathy (91 scans), 25-line raster confirmed fluid in 4 scans (P=.13) and 1 scan (P=

17 VO (123 scans) and BRVO (126 scans), 25-line raster confirmed fluid on 2 (P=.25) and 4 scans (P=.13),

18 Baseline SD-OCT scans included raster cubes centered on the optic nerve and macula, and

19 The design for a desired shape is made by raster-filling the shape with a 7-kilobase single-strand

20 In computer graphics, raster graphics encodes images on a single-pixel level,

21 drawings and scenes that can be rendered as raster-graphics images, allowing for easy generation of

22 Manual choroidal segmentation on a 25-raster horizontal scan protocol was performed.

23 Here the bioimaging approaches Raster Image Correlation Spectroscopy (RICS) and image-M

24 e cell within the same experiment by using a raster image correlation spectroscopy (RICS) based analy

25 Raster image correlation spectroscopy (RICS) is a noninv

26 fluctuation imaging methods (PIE-FI) such as raster image correlation spectroscopy (RICS) or number a

27 1 interactions by employing a combination of raster image correlation spectroscopy (RICS), fluorescen

28 imaging with correlation spectroscopy, as in raster image correlation spectroscopy (RICS), makes it p

29 This novel method, called raster image correlation spectroscopy (RICS), rapidly me

30 Using raster image correlation spectroscopy and number and bri

31 Here we apply an extended version of raster image correlation spectroscopy to determine direc

32 int FCS, photon-counting histogram analysis, raster image correlation spectroscopy, and two-color flu

33 fluorescence fluctuation approaches, notably raster image correlation spectroscopy, as tools to recor

34 ified by the novel fluorescent techniques of raster image scanning spectroscopy and number and bright

35 Using this cross correlation raster image spectroscopy method, specific locations in

36 enerate publication-quality vector graphics, rastered images and in-line streamed graphics for webpag

37 e (RPE/BM) layer imaged on the SD-OCT 5-line raster in normal subjects and in patients with papillede

38 trations from 100 nM down to <30 pM with PIE-raster lifetime image correlation spectroscopy (RLICS).

39 custom scan acquisition protocol of up to 13 raster lines of 9-mm scan length with automatic real-tim

40 s the acquisition of a Raman spectrum over a rastered macro spot.

41 s) and full-thickness MH (82 scans), 25-line raster missed focal traction (<1500 mum) and MH in 5 sca

42 ing of proteins from thin tissue sections in raster mode and discuss advantages (a 10-fold reduction

43 e composite image by collecting a predefined raster of matrix-assisted laser desorption/ionization ti

44 obtain spatially resolved spectra, by sample rastering or by 2D imaging, are introduced.

45 lled manner, and along a specific predefined raster path, covering a limited area.

46 d along an ad-hoc arbitrarily free-form, non-rastered path.

47 Furthermore, it is superior to the 25-line raster pattern at detecting early MH formation, while de

48 imaged 5 times, and each scan consisted of a raster pattern comprising 40 000 uniformly spaced A-scan

49 tion OCT instrument using a 200 x 200 A-scan raster pattern covering a 6 mm x 6 mm area centered on t

50 n spectra via a Raman microspectrometer in a raster pattern on a 0.5-microm grid and assembling pseud

51 of the labeled tissue by the laser beam in a raster pattern, the mass tags are liberated and recorded

52 Raster plots revealed a striking difference in the respo

53 how increasing both the number of pulses per raster point and the total acoustic power yielded corres

54 wo exposure parameters: number of pulses per raster point and total acoustic power.

55 on each eye, centered at the fovea, using a raster protocol.

56 Cirrus HD-OCT using the 512 x 128 horizontal raster protocol.

57 image analysis algorithms that are based on raster representation.

58 gh-throughput LIAD probe and an assembly for raster sampling of a LIAD foil were designed, constructe

59 Each raster scan covered a retinal area of 6 x 6 mm encompass

60 rence tomography (OCT) data were obtained as raster scan data (512 x 180 axial scans in a 6 x 6-mm re

61 hibit less scan distortion than conventional raster scan images.

62 Conventionally, raster scan methods are used to interrogate such librari

63 al scanner that performs a transillumination raster scan of the female breast in approximately 3 min.

64 epeated 3 times: 3-dimensional (3D) 6 x 6-mm raster scan of the optic disc and macula, radial, and li

65 A raster scan of the optic nerve and analysis of the retin

66 domain OCT technology enables higher density raster scan protocols and improved performance of en fac

67 Raster scan protocols enabled three-dimensional volumetr

68 ibrometry, and flow cytometry at a record 2D raster scan rate of more than 100 kHz with 27,000 resolv

69 e microscopy (to +/-4 nm), a two-dimensional raster scan to calibrate position detector response, and

70 T and fluorescence imaging by using only one raster scan.

71 ing fluctuation correlation spectroscopy and raster-scan image correlation spectroscopy analysis of l

72 This is different from the original raster-scan image correlation spectroscopy approach, whe

73 the idea of using Number and Brightness and Raster-scan Image Correlation Spectroscopy as methods to

74 Cross-correlation raster-scan image correlation spectroscopy revealed that

75 uorescence correlation spectroscopy (FCS) or raster-scan image correlation spectroscopy) or particle

76 tified by Number and Brightness analysis and Raster-scan Image Correlation Spectroscopy.

77 standard laser confocal imaging techniques (raster-scan mode) not only can we reach the temporal sca

78 Because in a raster scanned image successive pixels are measured at d

79 his article we describe a protocol to obtain raster scanned images with an Olympus FluoView FV1000 co

80 dimensional imaging systems frequently use a raster scanned laser to measure the range of each pixel

81 The electrode/light source was raster-scanned a finite distance above the sample surfac

82 Two-photon photolysis with raster-scanned femtosecond IR pulses gives the first thr

83 es a miniaturized resonant/nonresonant fiber raster scanner and a multielement gradient-index lens as

84 The miniaturized raster scanner is fabricated by mounting a commercial do

85 r both radial scan patterns when compared to raster scanning (P < .001 for both comparisons).

86 urrent pore and specific molecule imaging by raster scanning an alphaHL-based probe over a glass memb

87 ich require either long acquisition times or raster scanning and have a requirement for sufficient si

88 l, temporal control is easily attainable via raster scanning or random addressing, allowing for the s

89 s of healthy patients who had undergone a 31-raster scanning protocol on a commercial SD-OCT device w

90 t-of-plane growth rates can be controlled by raster scanning the coated tip across the substrate.

91 s of inhomogeneous polycrystalline solids by raster scanning them under a micro/nano focused polychro

92 pical of those used for crystal centering by raster scanning through an X-ray beam were sufficient to

93 age of 49 (22-79) years who underwent 1-line raster scanning with SD OCT were identified.

94 cal tissues can be formed by two-dimensional raster scanning, and functional parameters can be furthe

95 In this believed new method of modified raster scanning, as it acquires the image, the laser sca

96 ion to a small spot and probes the sample by raster scanning.

97 chemical image of the surface as compared to raster scanning.

98 Individual microcrystals are located by raster-scanning a several-micrometer X-ray beam across t

99 hoton efficiency have been with conventional raster-scanning data collection using single-pixel photo

100 Raster-scanning the radiation force over the object and

101 or an Er:YAG laser (350 mJ/pulse at 6 Hz) by raster-scanning the samples under a fixed handpiece or l

102 ow that fluorescence-fluctuation analysis of raster scans at variable timescales can provide this inf

103 For neovascular AMD (133 scans), 7 25-line raster scans confirmed subretinal/intraretinal fluid not

104 e of the choroid in healthy eyes from 1-line raster scans obtained using SD OCT.

105 of the technique have been compared with the raster scans showing that the algorithm provides reliabl

106 Sequential 6-line radial and 25-line raster scans were evaluated for intraretinal/subretinal

107 OCT raster scans were further analyzed regarding the central

108 Three-dimensional 6x6 mm macular cube raster scans were obtained with SS-OCT operating at 1050

109 T examination comprising a macular map, line raster scans, and en face images of the inner retinal su

110 avelength using repeated en face Doppler OCT raster scans, comprising 600 x 80 axial scans and coveri

111 fly-back distortion) present in conventional raster scans, it is not distortion-free.

112 SD OCT raster scans/fluorescein angiograms were obtained from 2

113 Specifically, given an environmental raster, SERAPHIM computes environmental "weights" for ea

114 A raster series of 100 B-scans separated by 60 microm was

115 e imaged on the fovea using Cirrus HD 1-line raster, Spectralis enhanced depth imaging (EDI), and RTV

116 is parameters like laser intensity and laser raster step size (spatial resolution in resulting image)

117 tional adaptations, we have used optogenetic raster stimulation to map the laminar distribution of GA

118 Removing the need to raster the optics in two directions significantly reduce

119 Continuous ceramic coatings are produced by rastering the laser beam over a sample specimen.

120 the ion abundances in spectra obtained while rastering the laser over the tissue.

121 Here, we adapt this raster/vector concept to a 2D colloidal system and reali

122 bstantially higher rates using both standard raster volume (20.0%, 90% confidence interval [CI] 8.2%-

123 concurrent imaging with a standard (61-line) raster volume and a 24-line radial pattern.

124 mall full-thickness MHs compared to standard raster volume scanning.

125 The effects of surface scanning mode (raster vs unidirectional scanning) and the constancy of

126 omplex, patterned stimuli into the projected raster, whose exact locations on the retina were recorde