Source: http://aoot.osa.org/oe/abstract.cfm?uri=oe-27-7-9868
Timestamp: 2019-04-19 22:25:51+00:00

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Optical fibers are widely used in bioimaging systems as flexible endoscopes that are capable of low-invasive penetration inside hollow tissue cavities. Here, we report on the technique that allows magnetic resonance imaging (MRI) of hollow-core microstructured fibers (HC-MFs), which paves the way for combing MRI and optical bioimaging. Our approach is based on layer-by-layer assembly of oppositely charged polyelectrolytes and magnetite nanoparticles on the inner core surface of HC-MFs. Incorporation of magnetite nanoparticles into polyelectrolyte layers renders HC-MFs visible for MRI and induces the red-shift in their transmission spectra. Specifically, the transmission shifts up to 60 nm have been revealed for the several-layers composite coating, along with the high-quality contrast of HC-MFs in MRI scans. Our results shed light on marrying fiber-based endoscopy with MRI to open novel possibilities for minimally invasive clinical diagnostics and surgical procedures in vivo.
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Fig. 1 Schematic showing preparation of the samples. (a) Hermetic coupling of the HC-MF to the pipette tip. The scanning electron microscopy (SEM) images denote the cross-section of the HC-MF. (b) The scheme of the PDDA/MNPs coatings formation. At first, the structure is washed twice by the deionized water. Then, polyelectrolytes and magnetite nanoparticles are adsorbed alternately onto the interior surface of the HC-MF by feeling the fiber with the polyelectrolyte solution for 10 min followed by washing with the deionized water after each adsorption step. The procedure is repeated to depose the desired number of bilayers.
Fig. 2 Magnetic resonance investigation of HC-MFs coated by nanocomposite bilayers. (a) Schematic of a sample: HC-MF is placed in the microcentrifuge tube filled with water. (b) 3D reconstruction obtained by T2 weighted (turbo spin-echo) MR scanning. HC-MFs are marked by yellow. (c) T1 weighted (spin-echo) MR image in the longitudinal plane. (d) T1 weighted (fast field echo) MR image in the longitudinal plane. The numbers ‘1’, ‘3’, and ‘5’ denote the number of nanocomposite bilayers in the sample. The lengths of the samples: ‘1’ – 0.9 cm; ‘3′ – 1.65 cm and ‘5′ – 0.8 cm.
Fig. 3 Schematics of the experimental setup for transmission characterization of HC-MF samples. The illumination of the broadband light source (halogen lamp) is launched into the HC-MF via an objective. The HC-MF is integrated in a smart cuvette (61-mm length). The input and output objectives and the cuvette are adjusted with three-axis motorized stages. The output spectrum is measured by the spectrometer Ocean Optics HR4000. The resulted data are analyzed by a personal computer.
Fig. 4 Characterization of optical transmission for HC-MFs. (a) The transmission spectrum of an unfilled HC-MF obtained by measurements (blue) and theoretical calculations (red). (b) Modifications in the selected HC-MF transmission window induced by coating with different numbers of bilayers (a high molecular weight) in comparison with the unfilled sample. (c) The transmission maximum as a function of the number of nanocomposite bilayers. The purple line denotes a theoretical prediction. The thickness of every nanocomposite bilayer is assumed to be 25 nm. The theoretical calculations have been performed for the TE-polarized light.
Fig. 5 Dependence of the refractive index for (a) the custom-made glass and (b) composite bilayers with MNPs on the light wavelength. In (a) points denote measurements, and the curve is an interpolation. The dispersion of the effective refractive index for the composite bilayers has been adopted from .
Fig. 6 Image of magnetite nanoparticles obtained by transmission electron microscopy (TEM).
(3) R= | M 21 M 11 | 2 .

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