ライフサイエンスコーパス: excitation light

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

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

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

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

5 has been handicapped by poor penetration of excitation light.

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

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

8 ticle orientation and on polarization of the excitation light.

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

24 Nonevanescent excitation light diminishes the optical sectioning effec

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

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

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

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

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

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

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

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

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

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

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

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

37 The excitation light intensity is reduced to minimize photob

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

39 This required low excitation light intensity to prevent GFP photobleaching

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

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

42 Excitation light is conducted to the microscope in a sin

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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

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