Abstract Brain iron is important for normal function and aberrantly high iron is often associated with neuroinflammation and neurodegeneration. Oligodendrocytes are a major source of iron in brain as are iron-laden activated macrophages and microglia. T2*-weighted MRI detected a large decrease in signal at the olfactory nerve layer (ONL) in normal young mice over the period of 3 to 12 weeks of age, consistent with iron accumulation in this region. This signal change was most prominent in the inner nerve fiber layer (iNFL). Iron histochemistry, ferritin immunohistology and electron microscopy showed that there was high iron and ferritin in the olfactory ensheathing cells (OECs) in the iNFL of ONL. The iron concentration in the iNFL was calculated to be approximately 2-3 mM based on MRI T2* relaxivity. The glomerular region near the high-iron iNFL had evidence of neuroinflammation markers of activated microglia and lipofuscin. Lipofuscin was found within the activated microglia as early as 6 weeks. In rats, MRI T2* signal loss in the ONL and high iron levels and lipofuscin were only detected in older rats (11 months) but not in young rats. These results indicate that mouse OECs develop high levels of iron at an early age. It is not clear if this iron is important for mouse OEC function or a result of phagocytic activity of OECs. The relation between iron and inflammation may be interesting to study in these young, healthy mice.
Collective cell behaviors in migration and force generation were studied at the mesoscopic-level using cells grown in a 3D extracellular matrix (ECM) simulating tissues. Magnetic resonance imaging (MRI) was applied to investigate dynamic cell mechanics at this level. MDCK, NBT2 and MEF cells were embedded in 3D ECM, forming clusters that then migrated and generated forces affecting the ECM. The cells demonstrated MRI contrast due to iron accumulation in the clusters. Timelapse-MRI enabled the measurement of dynamic stress fields generated by the cells, as well as simultaneous monitoring of the cell distribution and ECM deformation/remodeling. We found cell clusters embedded in the 3D ECM can exert translational forces to pull and push, as well as torque, their surroundings. We also observed that the sum of forces generated by multiple cell clusters may result in macroscopic deformation. In summary, MRI can be used to image cell-ECM interactions mesoscopically.
Manganese-block copolymer complexes (MnBCs) that contain paramagnetic Mn ions complexed with ionic–nonionic poly(ethylene oxide-b-poly(methacrylate) have been developed for use as a T1-weighted MRI contrast agent. By encasing Mn ions within ionized polymer matrices, r1 values could be increased by 250–350% in comparison with free Mn ions at relatively high fields of 4.7 to 11.7 T. MnBCs were further manipulated by treatment with NaOH to achieve more stable complexes (iMnBCs). iMnBCs delayed release of Mn2+ which could be accelerated by low pH, indeed by cellular uptake via endocytosis into acidic compartments. Both complexes exhibited good T1 contrast signal enhancement in the liver following intravenous infusion. The contrast was observed in the gallbladder due to the clearance of Mn ions from the liver to the biliary process. iMnBCs, notably, showed a delayed contrast enhancement profile in the gallbladder, which was interpreted to be due to degradation and excretion of Mn2+ ions into the gallbladder. Intracortical injection of iMnBCs into the rat brain also led to delayed neuronal transport to the thalamus. The delayed enhancement feature may have benefits for targeting MRI contrast to specific cells and surface receptors that are known to be internalized by endocytosis.
Abstract Introduction Postmortem MRI provides insight into location of pathology within tissue blocks, enabling efficient targeting of histopathological studies. While postmortem imaging of fixed tissue is gaining popularity, imaging tissue frozen at the time of extraction is significantly more challenging. Methods Tissue integrity was examined using RNA integrity number (RIN), in mouse brains placed between -20 °C and 20 °C for up to 24 hours, to determine the highest temperature that could potentially be used for imaging without tissue degeneration. Human tissue frozen at the time of autopsy was sealed in a tissue chamber filled with 2-methylbutane to prevent contamination of the MRI components. The tissue was cooled to a range of temperatures in a 9.4T MRI using a recirculating aqueous ethylene glycol solution. MRI was performed using a magnetization-prepared rapid gradient echo (MPRAGE) sequence with inversion time of 1400 ms to null the signal from 2-methylbutane bath, isotropic resolution between 0.3-0.4 mm, and scan time of about 4 hours was used to study the anatomical details of the tissue block. Results and Discussion A temperature of -7 °C was chosen for imaging as it was below the highest temperature that did not show significant RIN deterioration for over 12 hours, at the same time gave robust imaging signal and contrast between brain tissue types. Imaging performed on various human tissue blocks revealed good gray-white matter contrast and revealing subpial, subcortical, and deep white matter lesions typical of multiple sclerosis enabling further spatially targeted studies. Conclusion Here, we describe a new method to image cold tissue, while maintaining tissue integrity and biosafety during scanning. In addition to improving efficiency of downstream processes, imaging tissue at sub-zero temperatures may also improve our understanding of compartment specificity of MRI signal.
