ライフサイエンスコーパス: excitation light

1 . Pt.1. Identifying sources of nonevanescent excitation light).

2 alyte-mediated inner filtering of sub-330 nm excitation light.

3 ticle orientation and on polarization of the excitation light.

4 und to depend on wavelength and intensity of excitation light.

5 ferases have emerged, as they do not require excitation light.

6 inescence imaging of tumor in the absence of excitation light.

7 has been handicapped by poor penetration of excitation light.

8 nt and this is not observable with classical excitation light.

9 ing, is their ability to efficiently scatter excitation light.

10 t on the presence of an IFP that absorbs the excitation light.

11 entations that indicated the polarization of excitation light.

12 ng genetic targeting and/or spatially shaped excitation light.

13 l signals (roughly 10(-7)) compared with the excitation light(15,16).

14 ermine the number of photons of the incident excitation light absorbed by the sample, and the sample-

15 How deep the excitation light actually penetrates the sample is diffi

16 ET dynamic range, phototoxicity from the CFP excitation light and complex photokinetic events such as

17 t attaches to a urine catheter bag, emitting excitation light and detecting emission light of E. coli

18 n functions of absorption of energy from the excitation light and emission of that energy in the form

19 cy by controlling temporal properties of the excitation light and employed phasor analyses to FLIM an

20 bstantially on the polarization state of the excitation light and is highly tunable by external elect

21 ther factors were the improved absorption of excitation light and the increase of light extraction ra

22 he reaction proceeds only in the presence of excitation light and the rate and extent of reaction can

23 th of interrogation, owing to their need for excitation light and tissue autofluorescence.

24 ide of the beads and is fully exposed to the excitation light, and a strong increase in fluorescence

25 nce angle alters the interference pattern of excitation light, and hence the intensity of detected fl

26 mary wavelengths emitted in response to blue excitation light are within the spectrum of green light.

27 ch uses a single fiber to transport STED and excitation light, as well as collect the fluorescence si

28 d nonpolypoid adenomas were illuminated with excitation light at 351 and 364 nm.

29 Thus, excitation light at 490 nm impinging on the sensor is st

30 autofluorescence background and a paucity of excitation light at nonsuperficial locations.

31 s as cells flow in a fluid stream through an excitation light beam.

32 of the embedded microAPD to absorb scattered excitation light before it reached the detector.

33 alternating the modulation frequency of the excitation light between 300Hz and 10kHz.

34 oligomerization-dependent depolarization of excitation light by fused mNeonGreen fluorescent protein

35 surface in response to point illumination of excitation light by using a gain-modulated intensified c

36 approach for launching WGM resonances using excitation light coupled into a Dove prism.

37 Nonevanescent excitation light diminishes the optical sectioning effec

38 After exposure to excitation light encoded in n different ways, the 2-dime

39 if the cells express an IFP that absorbs the excitation light energy.

40 roscope that extends the wavelength range of excitation light, expands the number of simultaneously u

41 mtosecond pulse shaping was used to generate excitation light fields that were directed toward distin

42 w-coherence interferometric detection of the excitation light for depth-resolved aberration correctio

43 Hadamard-transform multiplexing of the excitation light from a 31-channel programmable light so

44 thin-film interference filter that prevents excitation light from inhibiting the fluorescence detect

45 ated scanning schemes are used to manage the excitation light going to and emission light coming from

46 owever, currently used short-wavelength (SW) excitation light has several limitations, including glar

47 ring is not the dominant source of far-field excitation light in objective-type TIRF, at least for mo

48 ging of fluorescent proteins (FPs) using red excitation light in the 'optical window' above 600 nm is

49 t different layers was altered by tuning the excitation light incident angle.

50 Blue excitation light induced a rapid (tau ~0.8 s), PLC-depen

51 ce generated by the substitution reduced the excitation light-induced photoactivation from the dark t

52 e imaging data, in particular under high (de)excitation light intensities of super-resolution imaging

53 s show a non-linear relationship between the excitation light intensity and mitotic arrest, and the f

54 The excitation light intensity is reduced to minimize photob

55 The effects of excitation light intensity on the kinetics of the bacter

56 quadratic dependence of DBP emission on the excitation light intensity shows the importance of the T

57 s better signal to noise for a given average excitation light intensity than sinusoidally-modulated i

58 This required low excitation light intensity to prevent GFP photobleaching

59 rate shows a non-linear relationship to the excitation light intensity, and a good correlation exist

60 dependence of the fluorescence signal on the excitation light intensity.

61 The cannula guides excitation light into the brain and the fluorescence sig

62 Excitation light is conducted to the microscope in a sin

63 oisson kinetics in the presence of scattered excitation light is resolved by filtering the prior mode

64 , extending calcium imaging to regimes where excitation light is undesirable or infeasible.

65 The encoded excitation light is used to irradiate the liquid sample

66 ective Si surface and the incidence angle of excitation light is varied by placing annular photomasks

67 phenomenon depending on the polarization of excitation light, is largely governed by the quantum geo

68 in vivo calcium imaging, but require intense excitation light, leading to photobleaching, background

69 iLLS) imaging, a technique that requires low excitation light levels and provides high background sup

70 ght at 830 nm in response to incident 785-nm excitation light modulated at 100 MHz.

71 diffuser transforms the high-peak-intensity excitation light near the fiber end into a broad light w

72 reflection fluorescence microscopy in which excitation light only penetrates several hundred nanomet

73 ion fluorescence (TIRF) microscopy, in which excitation light only penetrates several hundred nanomet

74 ignal from the plate by absorbing either the excitation light or the emission light.

75 We found the excitation light photoactivates as well as deactivates D

76 re overcome in two ways: (1) by limiting the excitation light power and gradually increasing the powe

77 lish a novel imaging modality which uses red excitation light (R-AF) and overcomes these drawbacks.

78 otoluminescence instruments by replacing the excitation light source (short duty cycle rectangular si

79 ark box containing a blue LED as a low-power excitation light source and a smartphone with a mobile a

80 ht filters were integrated for filtering the excitation light source and, thereby, increasing the con

81 NPs and the dyes allow the UCNPs to serve as excitation light source for the analyte-responsive BODIP

82 along with the excitation wavelength or the excitation light source.

83 of organic light emitting diodes (OLEDs) as excitation light sources for quantum dot-based fluoresce

84 rotation of the incident linearly polarized excitation light (technique referred to as PSHG).

85 amentally address the problem of propagating excitation light that is contaminating objective-type TI

86 ctral filter onto such devices (to block the excitation light) that has similar performance to the st

87 rised an optical fibre that delivered pulsed excitation light to an optical head at the distal end wi

88 UVR8 was not responsive to excitation light used to image cyan, green, or red fluor

89 rs of magnitude using HT multiplexing of the excitation light using a programmable light source.

90 The excitation light was 568 nm, and emission was detected o

91 roscopic capacity through fast tuning of the excitation light wavelength.

92 Using dark-field imaging of scattered excitation light we pinpoint the objective, intermediate

93 By varying the angle of incidence of the excitation light, we are able to obtain fluorescent cont

94 ing the wavefront of two-photon fluorescence excitation light, we developed Bessel-droplet foci for h

95 of the capillary leads to refraction of the excitation light, which affects the point spread functio

96 yet this traditionally relies on delivery of excitation light, which can trigger autofluorescence, ph

97 gs, material autofluorescence and leakage of excitation light, which deteriorates its detection limit

98 fluidic waveguide and efficiently guides our excitation light, which is butt-coupled from the side fa

99 sisted of a source that delivered 610-650-nm excitation light within a lighttight chamber, a 700-nm l