Zehong Cao, Andrew Z. Wang, Jing Huang, Malgorzata Lipowska, Hui Mao, Xiaodong Zhong, Lily Yang, Run Lin, Weiping Qian, Liya Wang, and Qiqi Yu
MAGNETIC IRON OXIDE NANOPARTICLES (IONPs) have been used as contrast agents of magnetic resonance imaging (MRI) for diagnostic imaging (1-3) and more recently for developing MRI-based molecular imaging probes in various biomedical applications, including cell tracking (4,5), biomarker targeted cancer imaging (6-8), and image guided drug delivery (9-11). IONPs, as a superparamagnetic agent, primarily shorten transverse relaxation times, ie, T2 and T2*, which leads to prominent signal decrease or "negative contrast" of targeted tissue on T2- and T2*-weighted images (12-14). The typical drawback of the T2- and T2*-weighted negative contrast is its poor sensitivity when used to study areas with low background signal. In addition, T2- and T2*-weighted imaging methods are also vulnerable to blooming artifacts and the partial volume errors from the effect of local magnetic inhomogeneity and high susceptibility of paramagnetic IONPs (15,16), making accurate localization and quantitative imaging of magnetic nanoparticles more difficult. It should also be mentioned that further improvement of negative contrast is limited by the threshold of the negative contrast which is the difference between the signal level of IONP affected area and signal intensity of zero (17). Therefore, conventional T2- and T2*-weighted imaging methods may not be able to take advantage of those magnetic nanoparticle probes with very high r2 relaxivity or increase of the dosage of administered IONPs because of the threshold of the negative contrast, as the maximal contrast that the negative contrast can reach is the signal intensity of zero. Therefore, a method of generating positive contrast from magnetic nanoparticles, ie, signal brightening, to improve the detection, and even quantification, of magnetic nanoparticles is desirable and has attracted increasing effort in translating magnetic nanoparticle imaging probes to broader applications (18-20). A number of approaches have been investigated to obtain positive contrast from IONPs, including ultrashort echo time (UTE) imaging (18,21,22), off-resonance saturation (ORS) techniques (23), sweep imaging with Fourier transformation (SWIFT) (24-27), phase contrast (28-30) and, most recently, adiabatic imaging (31,32). Among them, UTE imaging offers a relatively simple strategy by taking advantage of high longitudinal relaxivity r1 of IONPs while reducing the contribution of predominant T2 and T2* and spin dephase effects of IONPs that are also sources of imaging artifacts. With a very short echo time, typically below 0.1 msec, UTE imaging enables capturing signal enhancement from T1 effect with little influence of signal decay from the T2 and T2* effect, allowing for obtaining positive contrast on T1-weighted UTE images. Furthermore, the signal enhancement obtained from the UTE imaging is a function of T1 relaxation times of IONPs at different core sizes and concentrations in a certain range (18). A recent study by Girard et al (22) discussed the general strategy to optimize IONP detection sensitivity using UTE imaging. Through detailed computer simulation, imaging experiments on IONP phantoms in vitro and a proof-of-concept mouse model bearing human prostate tumors in vivo, it was shown that UTE imaging and subtraction of a longer echo signal from that of the UTE (SubUTE) were good approaches for imaging of IONP. In the present study, we report further investigation and application of UTE and SubUTE imaging for the detection and visualization of the receptor targeted IONP imaging probes in cancer xenograft mouse models using positive contrast enhancement. The main purpose was to demonstrate the capability of UTE imaging to obtain positive contrast from biomarker targeted magnetic nanoparticle probes selectively accumulated in the human pancreatic and breast cancer xenograft models in the mice in vivo.