pH-responsive theranostic nanocomposites as synergistically enhancing positive and negative magnetic resonance imaging contrast agents

Open Access



The rational design of theranostic nanoprobe to present responsive effect of therapeutic potency and enhanced diagnostic imaging in tumor milieu plays a vital role for efficient personalized cancer therapy and other biomedical applications. We aimed to afford a potential strategy to pose both T1- and T2-weighted MRI functions, and thereby realizing imaging guided drug delivery and targeted therapy.


Theranostic nanocomposites Mn-porphyrin&Fe3O4@SiO2@PAA-cRGD were fabricated and characterized, and the nanocomposites were effectively used in T1- and T2-weighted MRI and pH-responsive drug release. Fluorescent imaging also showed that the nanocomposites specifically accumulated in lung cancer cells by a receptor-mediated process, and were nontoxic to normal cells. The r2/r1 ratio was 20.6 in neutral pH 7.4, which decreased to 7.7 in acidic pH 5.0, suggesting the NCs could act as an ideal T1/T2 dual-mode contrast agent at acidic environments of tumor. For in vivo MRI, T1 and T2 relaxation was significantly accelerated to 55 and 37%, respectively, in the tumor after i.v. injection of nanocomposites.


The synthesized nanocomposites exhibited highly sensitive MRI contrast function no matter in solution, cells or in vivo by synergistically enhancing positive and negative magnetic resonance imaging signals. The nanocomposites showed great potential for integrating imaging diagnosis and drug controlled release into one composition and providing real-time imaging with greatly enhanced diagnostic accuracy during targeted therapy.


Theranostic nanoprobe T1/T2 dual-mode Magnetic resonance imaging Contrast agents Lung cancer 


The magnetic resonance imaging (MRI) technique has been introduced to clinic to provide multiplanar imaging for the soft tissues in the body without invasion. Because of its superb soft tissues imaging contrast, multidimensional imaging function, and absent of ionizing radiation, MRI is becoming increasingly available for clinical imaging [1]. In 2016, there were about 39 million diagnostic MRI procedures carried out in the United States, which presents an average annual growth rate of around 4% during the past 5 years [2].

Globally, contrast agents (CAs) are widely employed in the MRI, for which over 200 million doses had been administered [3]. The most frequently used reagents for contrast enhancement are gadolinium-based, such MRI contrast agents are representative T1 contrast agents that can effectively curtailing the T1 relaxation time of protons inside tissues by interactions with the neighboring contrast agent [4]. All clinically approved Gd-CAs are small molecules. For the reduction of toxicity, Gd3+ ions are usually chelated using DOTA (1,4,7,10-tetraazacyclododecane-1,4,7,10-tetraacetic acid) or DTPA (diethylene triamine pentaacetic acid) molecules [5]. Large amounts of Gd3+ ion chelates are injected during the clinical MRI procedure to yield millimolar concentrations required for the detection. On the other hand, nano-based CAs can be manufactured in small enough sizes to reach remote regions while simultaneously enabling surface functionalization that yields good biocompatibility, specific targeting, prolonged blood circulation time, and improved imaging effect as well as therapeutic efficacy [6, 7, 8, 9, 10].

Compared to traditional contrast agent, dual-mode T1/T2 MRI contrast agent can provide more accurate and detailed information associated with disease than single mode MRI contrast agent [11, 12, 13, 14, 15, 16, 17, 18, 19, 20]. The dual-mode T1/T2 MRI contrast agent has gained much attention, since it can give more precise and reliable diagnostic information by the enhanced contrast effects in both T1 imaging with high tissue resolution and T2 imaging with high feasibility on detection of a lesion [15]. Further, different from other multimodal imaging technologies (e.g., MR/optical, MR/PET) [21, 22, 23], dual-mode T1/T2 MRI can provide simultaneously imaging by adopting a single instrumental system, which could avoid the differences in penetration depths and spatial/time resolutions from multiple imaging devices [24].

However, the realization of dual-mode T1/T2 contrast agents has been challenging [12]. When combining the T1 and T2 CAs together, the strong magnetic coupling between them could perturb the relaxation effect of the paramagnetic T1 contrast agent, resulting in undesirable quenching of magnetic resonance signal [10]. To circumvent this problem, we have rationally constructed dual-mode T1/T2 CAs with releasable T1 contrast materials in the weak acidic tumor microenvironments. Therefore, the distance between T1 and T2 contrast materials could be increased after responsive releasing of T1 contrast materials to avoid the disturbance between them. As for the microenvironment in malignance, it is distinctly different from the normal tissues for several dimensions, which owes to the alterations in the metabolism of therioma [25]. The accumulation of lactic acid and H+, which is related to the upregulated anaerobic glycolysis in tumorigenesis and the excessive transport of hydrogen ions from tumor cells to the outside, leads to the declined extracellular pH values and the acidic microenvironment in tumor tissue. The variation in the pH has been proved to be able to serve as an effective design for cancer diagnosis and treatment by many previous researches [26, 27, 28, 29].

Therefore, we have designed a novel pH-responsive theranostic nanoprobe with Fe3O4 nanoparticles in core (T2 contrast agent) and water soluble Mn-porphyrin (T1 contrast agent) in shell, which present MRI signal “OFF” in the normal tissue and turn both T1 and T2 signal “ON” in the acidic tumor tissue (Scheme 1). The PAA coated SiO2 layer can be used as a pH-responsive vehicle for loading T1-contrast agent and anticancer drug DOX, and c(RGDyK) was chosen as the targeting group. The distance between Mn-porphyrin and Fe3O4 nanoparticles could be increased after responsive-releasing of Mn-porphyrin to avoid the disturbance between T1 and T2 contrast agents. Such design of Mn-porphyrin&Fe3O4@SiO2@PAA-cRGD nanocomposites (designated as Mn-IOSP NCs) affords a potential strategy to pose T1- and T2-weighted MRI functions, and thereby realizing imaging guided drug delivery and targeted therapy.
Scheme 1

Schematic illustration for the formation, release and imaging process of DOX-loaded Mn-IOSP NCs



Poly(acrylic acid) (PAA, Mw = 2000), N-hydroxysuccinimide (NHS), and 1-(3-dimethylaminopropyl)-3-ethyl carbodiimide hydrochloride (EDCI) were obtained from Aladdin. Tetraethyl orthosilicate (TEOS) and Igepal CO-520 were purchased from Sigma-Aldrich. 4-dimethylaminopyridine (DMAP), manganese (II) acetate, N-cetyltrimethylammonium chloride (CTAC) and triethanolamine (TEA) were purchased from Sinopharm Chemical Reagent Co., Ltd. c(RGDyK) peptides (cRGD) was purchased from GL Bioche. All other reagents were analytical grade and used without further purification.


1H and 13C NMR spectra for compounds were obtained in DMSO-d 6 , using a Bruker AMX-500 NMR spectrometer. Transmission electron microscopy (TEM) images were obtained on a HITACHI H-7000 FA transmission electron microscope. High-resolution mass spectrometry (HR MS–ESI) spectra were recorded on a Bruker micro TOF-Q instrument. The magnetic properties were measured at 300 K with a vibrating sample magnetometer (SQUID-VSM, Quantum Design, American). In vitro fluorescence images of cells were recorded on a confocal laser scanning microscope (CLSM, Nikon, Japan). The surface areas were measured by an ASAP-2020 physisorption apparatus (Micromeritics, American). The UV–Vis absorption spectra were determined by an Evolution 220 spectrophotometer (Thermofisher Scientific). The size distributions and zeta potentials were measured by a Malvern Zetasizer 90. The metal contents in cells and tissues were tested by ICP-MS (FLEXAR NEXLON300X).

Preparation of Mn-porphyrin&Fe3O4@SiO2@PAA-cRGD (Mn-IOSP)

Fe3O4 NPs were prepared by a thermal decomposition reaction with ferric oleate complex as precursor, oleic acid as reductant, and trioctylamine as solvent at a reaction temperature of 340 °C [30]. 1.8 g of ferric oleate and 0.624 g of oleic acid were dissolved in the trioctylamine (10 mL). The mixture was heated gradually from room temperature to 340 °C and kept in this temperature for 1 h in N2 atmosphere. Fe3O4@nSiO2 was synthesized through a typical water-in-oil microemulsion method by using nonionic surfactant Igepal CO-520 [31]. For the synthesis of Fe3O4@nSiO2@mSiO2 [32], Fe3O4@nSiO2 was added into aqueous solution containing CTAC and TEA and stirred to be well-mixed, then TEOS was added into the solution and the hydrolysis reaction was carried out. After the reaction, the nanoparticles were purified by repeated washing and reprecipitation. For preparation of Fe3O4@SiO2@PAA-cRGD, we first synthesized PAA-cRGD. Then the Fe3O4@SiO2@PAA-cRGD NPs were synthesized from the change of the interfacial energy between PAA, Fe3O4@SiO2 NPs and the solvent [33]. Detailed experimental steps were presented in Additional file 1: S1.

The manganese porphyrin compounds 1 (Mn-porphyrin) was synthesized following the reported literature with some modifications [34]. Tetrakis (4-carboxyphenyl) porphyrin (TCPP, 94 mg) was mixed with EDCI (143 mg) and NHS (90 mg) in DMF and then stirred under nitrogen. After 1 h, a DMF solution containing N-boc ethylenediamine (151 mg) and DMAP (118 mg) was added into the mixture above-mentioned and continued for 1-day stir. The mixture was dealt with 100 mL brine before filtering. The N-Boc protected porphyrin (5, 10, 15, 20-tetrakis 2-[(4-tert-butyl benzamido)] ethyl carbamate] porphyrin) was separated with impurities through column chromatography using a mobile phase of DCM: methanol 90:10. The product was mixed with excess manganese acetate in methanol and reacted at 70 °C for 12 h with stirring. The N-Boc protected Mn-BOC-porphyrin (manganese 5, 10, 15, 20-tetrakis 2-[(4-tert-butyl benzamido) ethyl carbamate] porphyrin) was also purified through column chromatography using a mobile phase of DCM:methanol 90:10. Then the N-Boc protected Mn-BOC-porphyrin (30 mg) was added into CH2Cl2 with stirring for 30 min under 0 °C. HCl (4 M, 0.5 mL in dioxin) was dripped into the mixture before a 12-h stir, and the solution kept 0 °C for the duration of dripping. Then the reaction product was poured into diethyl ether and filtered. The precipitate was washed by some diethyl ether before collecting. The 1H NMR, 13C NMR, MS, UV spectra and structures for porphyrin-compounds were showed in Additional file 1: S2, including the Figs. S1–S11.

For the preparation of Mn-IOSP, 5 mg of Fe3O4@SiO2@PAA NPs were dissolved in a mixed solution containing 5 mL water and 45 mL isopropanol. Mn-porphyrin aqueous solution (1 mL, 10 mg/mL) was mixed into the solution before being shaken for 24 h. Finally, the desired Mn-IOSPs were gained through centrifugation separation and purification with PBS buffer.

In vitro cytotoxicity test

The A549 non-small-cell lung cancer cells were seeded into 96-well plates for 5000 cells/well before 1-day culture. For the following 4-h incubation, the medium was changed to RPMI-1640 mediums dispersing Fe3O4@SiO2@PAA NCs, Mn-IOSP NCs or DOX loaded NCs with pre-established concentrations, respectively. The NCs solution was then sucked out and unabsorbed NCs were removed by rinsing with fresh PBS twice. For an additional 44-h culture, 100 μL of medium without NCs was added into every plate. The cell viabilities were tested by MTT assays with a plate reader (Molecular Devices, USA). The cell viabilities were calculated basing on the ratio of absorbance value of treatment group to that of control group. Detailed cell culture process was showed in Additional file 1: S3.

In vivo MRI

Transplantation tumor models of non-small-cell lung cancer were established on the 4- to 5-week-old BALB/c male nude mice through subcutaneous injection of A549 cells. The mice were reared for another 2 weeks after subcutaneous injection of 1 × 107 A549 cells per mouse in hind leg. T1- and T2-weighted MR images were performed on a 7.0 T animal MRI scanner (Bruker BioSpec 70/20 USR). Mn-IOSP NCs were intravenous injected into mice, and images were acquired both before and after injection. Specific parameters for images were showed in Additional file 1: S4.

In vitro MR contrast properties

A549 cells were used for validating the in vitro MRI capacity of the Mn-IOSP NCs. After 1-h incubation with the indicated concentrations of Mn-IOSP NCs, the NCs solution was then sucked out and unabsorbed NCs were removed by rinsing with fresh PBS. Then the cells were digested and then collected with 500 μL PBS. T1- and T2-weighted MR images were performed on a 9.4 T NMR spectrometer (Bruker Avance 400, Ettlingen, Germany) equipped with microimaging gradient coils. Specific parameters were showed in Additional file 1: S4.

To measure the longitudinal (r1) and transverse (r2) relaxation parameters of Mn-IOSP NCs, different concentration points of Mn-IOSP NCs were dispersed in different buffer solutions (pH 7.4, 6.5, 5.0). T1- and T2- relaxation times of the solutions were tested by the 7.0 T animal MRI scanner using the same sequences as in vivo MRI after 1-day incubation at 37 °C.

Results and discussion

Fabrication and characterization

The formation of the multifunctional magnetic NCs could be divided into 4 steps: (1) the synthesis of the OA-coated Fe3O4 NPs, (2) the successive formation of dense SiO2 and mesoporous SiO2 shells on OA-coated Fe3O4 NPs, (3) the coating of PAA-cRGD upon the as-synthesized Fe3O4@SiO2 NPs, (4) the loading of Mn-porphyrin into the NPs. Finally, the Mn-IOSPs NCs were obtained and employed as a dual modality imaging contrast agent for T1 and T2. TEM images in Fig. 1a showed the size of the initial OA-Fe3O4 NPs were around 30 nm. Then the hydrophobic NPs were coated with dense SiO2 to form hydrophilic Fe3O4@nSiO2 via a controlled sol–gel reaction (Fig. 1b). The TEOS was hydrolyzed and wrapped around the Fe3O4@nSiO2 to form Fe3O4@nSiO2@mSiO2 (Fig. 1c). The PAA-cRGD was synthesised successfully and validated by UV absorption spectrum (Fig. 2a). PAA-cRGD and cRGD show same typical absorption peaks at 274 nm, while PAA has no obvious absorption peaks there. The encapsulation of PAA-cRGD shells outside Fe3O4@SiO2 may be associated with the hydrogen bond between the carboxyl groups of PAA and the hydroxyl groups of SiO2, and the transformation of interfacial energy between shells, nanoparticles and solvent during the loading process, which has a tendency to cause the smallest interfacial energy [33]. We can see thin layers on the surfaces of the Fe3O4@SiO2@PAA-cRGD NPs (Fig. 1d), suggesting that the PAA was successfully coated on the as-synthesized NPs. The Fe3O4@SiO2@PAA-cRGD NPs show hydrodynamic diameters of 164.2 nm and zeta potentials of − 32.2 mV compared to the 140.0 nm and − 17 mV of Fe3O4@mSiO2 (Additional file 1: S5, including Table S1 and Figs. S12–S16), which also confirm the successful coating of PAA shells on silica. To verify the mesoporous properties of nanoparticles, the nitrogen adsorption/desorption isotherm of Fe3O4@SiO2@PAA-cRGD NPs was observed (Fig. 2b). It could be calculated that the Fe3O4@SiO2@PAA-cRGD NPs are with high specific surface area (SBET, 349 m2/g) and large cumulative pore volume (Vp, 0.712 cm3/g), and exhibit an intensive pore diameter peak at 3.5 nm. All these results above proved the feasibility of the Fe3O4@SiO2@PAA-cRGD NPs to be an appropriate carrier for T1-contrast agents and drugs. Figure 2c showed the FT-IR spectrum of the nanoparticles. New signals at 1708 cm−1 from carbonyl groups of PAA is also clearly observed in the Fe3O4@SiO2@PAA-cRGD NPs, which further proves the formation of PAA shell. The magnetic hysteresis curves are shown in Fig. 2d to evaluate the saturation magnetization of Fe3O4@SiO2@PAA-cRGD NPs. At 300 K, the neglectable remanence indicates that the NPs did not possess a net magnetic moment. The measured saturation magnetization (Ms) was ~ 9.7 emu/g, suggesting their probability for improving the effect of MRI and magnetic targeting drug delivery [35].
Fig. 1

TEM images for nanoparticles: a OA-Fe3O4 NPs, b Fe3O4@nSiO2 NPs, c Fe3O4@nSiO2@mSiO2 NPs, d Fe3O4@SiO2@PAA-cRGD NPs. The scale bars are 50 nm

Fig. 2

Characterization of nanoparticles: a UV–Vis absorption spectra of cRGD, PAA-cRGD and PAA in water, b N2 adsorption (hollow)–desorption (solid) isotherms (inset: pore size distribution from adsorption branch) of Fe3O4@SiO2@PAA-cRGD NPs, c FT-IR spectra of Fe3O4@SiO2 NPs, Fe3O4@SiO2@PAA-cRGD NPs and PAA, d Magnetization vs. applied magnetic field for Fe3O4, Fe3O4@SiO2, and Fe3O4@SiO2@PAA-cRGD NPs at 300 K

In vitro fluorescence and UV–Vis analysis

The capacity of nanoparticles for loading drug and Mn-porphyrin has been evaluated. The loading efficiency and releasing rate of modal drug doxorubicin hydrochloride (DOX) for Fe3O4@SiO2@PAA-cRGD NPs was evaluated by fluorescence spectrophotometer at different time points emission at 590 nm and excitation at 495 nm. AAS and UV spectra were used for the quantification of Mn-porphyrin in the NCs. Detailed drug loading and release procedures were showed in Additional file 1: S6. After the loading process of the Mn-porphyrin and DOX with the nanoparticles, the desired NCs were gained through centrifugation separation and the concentrations of Mn-porphyrin and DOX in supernatant were determined. The loading efficiency of DOX could be up to 90% without adding Mn-porphyrin. The excellent efficiency was benefited from the synergistic loading function of both PAA-cRGD and mSiO2 shells. The loading efficiency of Mn-porphyrin in Mn-IOSP NCs calculated from UV spectra was 75%, which was approximately in accordance with the metal content ratio tested by AAS (7.4/1 for iron/manganese). The structure of Mn-porphyrin has 4 amino groups and would be easy to be positively charged in the pH from 5.0 to 7.4. The strong electrostatic attraction existed between the negatively charged PAA and silica pores and the Mn-porphyrin molecules. The possible interaction of π–π stacking between the Mn-porphyrin molecules and hydrogen bonds would make it also easy to exist in the PAA shells and silica channels. When Mn-porphyrin was added into the solution simultaneously with DOX, the loading efficiency changed to 57% for DOX and 52% for Mn-porphyrin. The loading efficiencies of both DOX and Mn-porphyrin decreased when Mn-porphyrin and DOX was added into the solution simultaneously, which indicated the competition between Mn-porphyrin and DOX in loading process for the similar mechanism in the loading process.

For investigating the pH-triggered controlled release property of the DOX&Mn-IOSP NCs, samples were dispersed in different release media to simulate the release behavior in different physiological environments. As shown in Fig. 3a, only 18% DOX was released from DOX&Mn-IOSP NCs at pH 7.4 for a period of 48 h at 37 °C, while the release rate could reach 75% at pH 5.0, indicating the good pH sensitivity of Mn-IOSP NCs. This is because DOX is positively charged in the three pH of study, and the abundant carboxyl groups in PAA are protonated with the decreasing of pH in the medium, which weaken the electrostatic interaction with positively charged DOX [36]. For investigating the in vitro release property of the Mn-porphyrin, equal amounts of Mn-IOSP NCs were dispersed in different release media to simulate the release behavior (Fig. 3b). In the pH 5.0, the release rate could reach up to 88%, and the release has gone quickly at the first 2 h. These evidences suggest that the release rate of model molecules DOX and Mn-porphyrin from NCs might be accelerated in the mildly acidic environments of tumor areas compared to the neutral physiological environment of normal tissue. When the Mn-porphyrin released from the NCs, the Mn-porphyrin could go apart from the interference of the strong magnetic field induced by Fe3O4 core [7] and activated the T1 contrast ability of Mn-IOSP NCs. The ability increased with the rising release rate of Mn-porphyrin, which was along with the decrease of pH. As a result, the synthesized Fe3O4@SiO2@PAA-cRGD NCs and Mn-IOSP NCs can be a promising platform for pH-response MRI and drug delivery during cancer treatment.
Fig. 3

Fluorescence analysis and UV–Vis of nanoparticles: a pH-dependent (pH 5.0, 6.5, 7.4) drug release of DOX&Mn-IOSP NCs, b pH-dependent (pH 5.0, 6.5, 7.4) release of Mn-porphyrin in Mn-IOSP NCs, c fluorescence confocal micrographs of DOX&Mn-IOSP NCs (with or without modified with cRGD) and free DOX incubated in WI38 cells or A549 cells, the scale bars are 50 μm

The confocal fluorescence imaging was also employed to analyse the NCs (Fig. 3c). In the A549 cells which were incubated with DOX&Mn-IOSP NCs, strong red fluorescence was displayed in the cytoplasm and strong blue fluorescence was obtained in the nucleus. The blue fluorescence occurred by staining with DAPI and excited with a 405 nm laser, and the red fluorescence excited with a 488 nm laser from DOX indicates the successful entrance into the cell and the release of the DOX of the DOX&Mn-IOSP NCs. To validate the red fluorescence in the cell was caused from the entrance of NPs rather than only the DOX previously released, A549 cells was incubated with free DOX and both red and blue fluorescence was displayed in the nucleus, which was different from cells incubated with NPs, declaring the two different ways for the DOX coming into cells.

Tumor targeting ability of the Mn-IOSP NCs was investigated by CLSM following the incubation of A549 cells and WI38 cells with the DOX&Mn-IOSP NCs. The red fluorescence (attributed to DOX) in A549 cells incubated with DOX&Mn-IOSP NCs was distinguishably higher than that of NCs without modified with c(RGDyK), and the fluorescence intensity in A549 cells was obviously higher compared with that in non targeted WI38 cells under same incubation condition (Fig. 3c), which verified the specific targeting ability of NCs. DOX fluorescence was observed mostly in the cytoplasm instead of the cell nuclei, suggesting that DOX-loaded NCs were internalized and release DOX into the cytoplasm after uptake by A549 cells.

Relaxivity measurements

To evaluate the capacity of Mn-IOSP NCs as T1/T2 dual-mode contrast agents, a 7.0 T animal MRI scanner was used and both longitudinal (r1) and transverse relaxivities (r2) were calculated. The content of iron and manganese in Mn-IOSP NCs were determined by atomic absorption spectrometry (AAS). Iron content in Mn-IOSP NCs was about 16 wt% and atomic content of iron was 7.4 times that of manganese in Mn-IOSP NCs. Samples of the Mn-IOSP NCs in different pH value of buffer containing various metal concentrations were scanned. The longitudinal relaxivity (r1) and transverse relaxivity (r2) were gained from the slope of the fitting line between the reciprocal of relaxation time and Mn concentration curves (Fig. 4a). We observed that the r1 increased while the r2 decreased with the decreasing pH value of buffer, which indicates the NCs exhibited a stimuli-response T1/T2 MRI enhancement. The ratio of r2/r1 reached as high as 20.6 at pH 7.4, which manifested a more dominant effect of T2-enhancement than T1 in this condition. The Fe3O4 in core would generate inhomogeneous magnetic field to influence the T2 effect of the water molecules around [7, 37]. The strong local magnetic field generated from the Fe3O4 ensured the properties of Mn-IOSP NCs for acting as T2 contrast agent. The strong magnetic field induced by Fe3O4 core would disturb the relaxation process of the Mn-porphyrin when they are close enough to generate magnetic coupling [12, 38], and the changes in distance between Mn-porphyrin and Fe3O4 cores after release attenuated the coupling effects. These factors contributed to the quenching of the T1 signal in high pH environment. We hypothesize two synergetic components that led to the abatement of r2 after Mn-release. First, the geometrical confinement effect of channels in silica to Mn-porphyrins vanished after release [39, 40, 41]. Water molecules inside mesoporous structure of Mn-IOSP NCs can be slowed down because they bind to the slowly moving complexes in the pore or undergo the geometrical restraints of the proximate pore walls [41]. The restriction of water inside the channels might lead to reduction of mobility for the hydration layer, which was conducive to relaxivity [39]. Further, the high surface area-to-volume ratio and water accessibility through the pores allows for an efficient T1/T2 dual-mode MR contrast agent due to the incorporated complex between H2O and Mn-porphyrin. Second, the concentrated Mn paramagnetic centers disappeared after release. When the Mn-porphyrins were loaded in the channels, the substantial quantity of Mn potentially create concentrated Mn paramagnetic centers, leading to an effective magnetic field gradient that dephases water protons and shortens T2 in strong fields [39, 40, 42]. However, when the pH decreased, these effects would fade with the release of Mn-porphyrin into solution, which led to a decline of r2. The enhancement of the T1 relaxivity and the receding T2 relaxivity of Mn-IOSP NCs via the decreasing pH value of buffer may be due to the additional releasing of Mn-porphyrin from the mesoporpous. There was no commercial T1/T2 dual mode contrast agent and commercial Mn-based T1 contrast agent yet. MnxOy structures have often been reported as Mn-based CAs [43, 44, 45, 46]. The r 1 (4.25/mM/s, pH 5.0) and r 2 (42.1/mM/s, pH 7.4) of Mn-IOSP was higher than that of the MnO (0.3/mM/s, 3.0 T) and HMnO (1/mM/s, 11.7 T) [43, 44], and was comparable to the T1/T2 dual mode contrast agent of Fe3O4@SiO2(Gd-DTPA)-RGD NPs (4.2/mM/s for r 1 and 17.4/mM/s for r2, 3.0 T) and manganese oxide/MSNs (3.1 mM/s for r1 and 46.1/mM/s for r2, 3.0 T) which previously reported [18, 47]. Although the r2 was not as high as that of the commercial Feridex (108/mM/s, 3.0 T), the Mn-IOSP NCs offer unique features to act as T1-positive/T2-negative bimodal contrast agents and to some extent could break the restrictions of ordinary one-mode contrast agents. So far as we know, few studies have focused on exploring responsive T1/T2 dual-mode CAs, much less combination with pH-responsive imaging diagnosis and tumor targeting drug controlled release into one composition. The releasing of Mn-porphyrin actived the contrast ability of Mn-IOSP NCs from single-mode to dual-mode, and guaranteed the capacity for accurate imaging in tumor sites. When the r2/r1 ratio reduced from 20.6 (pH 7.4) to 7.7 (pH 5.0), the increasing T1-contrast enhancement via the releasing of the Mn-porphyrin suggested the Mn-IOSP NCs could act as an ideal T1/T2 dual-mode contrast agent at acidic environments of tumor areas [14]. These results demonstrated that Mn-IOSP NCs can act as T1-positive/T2-negative bimodal contrast agents.
Fig. 4

Relaxivity measurements and cell metal content determination of Mn-IOSP NCs: a the longitudinal relaxivity and transverse relaxivity of Mn-IOSP NCs at different pH (5.0, 6.5, 7.4), plots for 1/T1 and 1/T2 vs. Mn concentration, b iron and manganese content in A549 cells due to the uptake of NCs which modified with PAA-cRGD or PAA, c iron and manganese content in A549 cells due to the uptake of Mn-IOSPs in different concentrations, d T1- and T2-weighted MRI for A549 cells incubated with Mn-IOSP NCs at different concentrations, e in vivo T1- and T2-weighted MRI acquired before and after i.v. injection of Mn-IOSP NCs, the tumor sites were circled roughly with white dotted lines

For further demonstration of the T1 and T2-effect and cellular uptake of the Mn-IOSP NCs, in vitro T1-weighted and T2-weighted MR images of A549 cells were observed after incubated with NCs for 1 h. Quantitative analysis of Fe and Mn in the incubated cells has also been carried out by ICP-MS to help to quantify the cell uptake. The contents of metal in cells after incubation with NCs modified with PAA-cRGD or PAA were analyzed by ICP-MS. The concentrations of both manganese and iron were higher in the cells incubated with the NCs modified with c(RGDyK) than the NCs without c(RGDyK) (Fig. 4b). In addition, the higher of the NCs concentration incubated with cells, the higher the signal intensities of manganese and iron were tested by ICP-MS (Fig. 4c). The results were consilient with the experiments of in vitro cell MRI. As shown in Fig. 4d, the T1 and T2-weighted MRI contrast effect correlated with the concentration of the Mn-IOSP NCs. The Mn-IOSP NCs displayed an enhancement in the T1-weighted MR signal, and a reduction in T2-weighted MR signal with the increasing Mn concentration. This confirmed that the Mn-IOSP NCs could be utilized as efficient T1 and T2 dual-mode contrast agents for A549 tumor cells.

To further validate the ability of Mn-IOSP NCs as T1/T2 dual-mode MRI agents, we conducted the in vivo MRI of mice which transplanted subcutaneous A549 tumor before and after injecting the Mn-IOSP NCs (200 μL, [Mn] = 2 mM) via the tail vein. As shown in Fig. 4e, the T1 and T2 relaxation time in mice-transplanted tumor areas was obviously fasted after injection of Mn-IOSP NCs, and T1-weighted signal was enhanced whereas T2-weighted signal was reduced. Compared to the images without injection of NCs, the most powerful acceleration in tumor signal for T1 was 55%, and for T2 was 37%, both after 3 h injection of the NCs. T1-weighted images took on brighter effects in the region of A549 tumor after injection, whereas darker effects were exhibited in T2-weighted images. In addition, after 12 h injection, the signal intensity recovered to some extent. The biodistributions of NPs were evaluated in A549 tumor-bearing mice after 3 h intravenous injection of Mn-IOSP NCs (details in Additional file 1: S7). Both manganese and iron showed significant tumor accumulation (Additional file 1: Fig. S17), which were consistent with the MR images. The Mn-IOSP NCs with appropriate residence time and controlled release performance show the remarkable potential for in vivo MRI for tumor. The accumulation of Mn-IOSP NCs in tumor might realize through the EPR effect and the targeting effect of c(RGDyK).

These evidences showed that the synthesized Mn-IOSP NCs exhibited highly sensitive MRI contrast function no matter in solution, cells or in vivo, and comprehensive analysis from the information of both T1/T2 imaging could be conducted, which to some extent breaks the restrictions of ordinary one-mode contrast agents.


Cytotoxicity of Mn-IOSP NCs in vitro was judged through standard tetrazolium dye (MTT) based colorimetric assay for viability of A549 cell. In the tested range of concentration, the cytoactive of A549 cells had not declined significantly after the incubation with Fe3O4@SiO2@PAA-cRGD NPs and Mn-IOSP NCs (Fig. 5a). The cell viability still remained about 80% after incubated with Mn-IOSP NCs at a very high dose of 500 μg/mL NCs, indicating that the NCs are biocompatible and minimally cytotoxic in the given concentration range. After incubation with DOX-loaded NCs, the cell viabilities significantly decreased compared to the Mn-IOSP NCs and Fe3O4@SiO2@PAA-cRGD NCs of same concentrations. These results demonstrate little toxicity of our NPs and NCs as dual contrast agents. In addition, the effect of DOX-loaded NCs was close to the free DOX compared with the cytotoxicity assay of an equal concentration of DOX alone, for which confirms the feasibility of the NCs as drug carriers systems.
Fig. 5

Biotoxicity of nanoparticles: a cell viability assays of A549 cells treated with different samples, *for samples calculated by DOX content with the upper abscissa, b H&E staining images of histological sections with major organs after 48 h injection of 200 μL Mn-IOSP NCs (experimental group) or 200 μL PBS (control group)

Hematoxylin and Eosin (H&E) staining method was used to assess the toxicity of the developed Mn-IOSP NCs in vivo. Mice treated with Mn-IOSP NCs or PBS (as control) were sacrificed post 48 h i.v. injection. Apparently, we can see from Fig. 5b, no obvious damage or abnormalities can be seen in the major tissue sections such as heart, liver, spleen, lung, and kidney after 48 h i.v. injection of the NCs, which suggests that the Mn-IOSP NCs have good organ compatibility.


In conclusion, we have developed a multifunctional nanocomposite of Mn-porphyrin&Fe3O4@SiO2@PAA-cRGD for dual-modal bioimaging and drug-loading capacity as a result of our studies. Compared to previous multifunctional contrast agents, the proposed nanocomposite integrates the advantages of synergistically enhancing positive and negative magnetic resonance imaging signals, no matter in solution, cells or in vivo. The r2/r1 ratio was 20.6 in neutral pH 7.4, which decreased to 7.7 in acidic pH 5.0, suggesting the NCs could act as an ideal T1/T2 dual-mode contrast agent at acidic environments of tumor. Conjugation with RGD enables the functional imaging probe for high A549 cellular uptake and targeted tumor imaging in vivo. The findings of this study illustrate that Mn-porphyrin&Fe3O4@SiO2@PAA-cRGD is a potentially useful tool for multimodal molecular imaging of cancer cells as well as a drug delivery platform for therapeutic agents.


Authors’ contributions

XH, SC and XZ designed the experiments. XH and LL conducted the preparation and characterization. YY, WR and XH performed the relaxivity measurements and data analysis. XH performed the toxicity and fluorescence analysis. XH and SC wrote the paper. XZ and ML contributed reagents, materials and analysis tools. All authors read and approved the final manuscript.


X. Zhou thanks the National Program for Special Support of Eminent Professionals (National Program for Support of Top-notch Young Professionals).

Competing interests

The authors declare that they have no competing interests.

Availability of data and materials

All data supporting this study are included in this published article and its additional information files. All mouse experimental procedures were performed in accordance with the Regulations for the Administration of Affairs Concerning Experimental Animals approved by the State Council of People’s Republic of China.

Consent for publication

All authors agree to publish this manuscript.

Ethics approval and consent to participate

All mouse experimental procedures were performed in accordance with the Regulations for the Administration of Affairs Concerning Experimental Animals approved by the State Council of People’s Republic of China.


This work was supported by the National Natural Science Foundation of China (21575157, 81227902 and 81625011), and Key Research Program of Frontier Sciences, CAS, Grant NoQYZDY-SSW-SLH018.

Publisher’s Note

Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.

Supplementary material

12951_2018_350_MOESM1_ESM.docx (6.6 mb)
Additional file 1. Additional figures, experimental details and parameters. Part S1: Preparation of Fe3O4@SiO2@PAA-cRGD; part S2, including the Fig. S1–S11: 1H NMR, 13C NMR, MS, UV spectra and structure for compounds; part S3: Cell culture; part S4: Specific parameters of MR contrast properties test; part S5, including Table S1 and Fig. S12–16: Hydrodynamic diameters of the nanoparticles tested by DLS; part S6: Drug loading and in vitro release; part S7, including Fig. S17: Biodistributions tested by ICP-MS.


  1. 1.
    Lee N, Hyeon T. Designed synthesis of uniformly sized iron oxide nanoparticles for efficient magnetic resonance imaging contrast agents. Chem Soc Rev. 2012;41:2575–89.CrossRefGoogle Scholar
  2. 2.
    IMV. 2016 MR market outlook report. 2017. Accessed 10 Oct 2017.
  3. 3.
    Hao DP, Ai T, Goerner F, Hu XM, Runge VM, Tweedle M. MRI contrast agents: basic chemistry and safety. J Magn Reson Imaging. 2012;36:1060–71.CrossRefGoogle Scholar
  4. 4.
    Hermann P, Kotek J, Kubicek V, Lukes I. Gadolinium(III) complexes as MRI contrast agents: ligand design and properties of the complexes. Dalton T. 2008;23:3027–47.CrossRefGoogle Scholar
  5. 5.
    Caravan P, Ellison JJ, McMurry TJ, Lauffer RB. Gadolinium(III) chelates as MRI contrast agents: structure, dynamics, and applications. Chem Rev. 1999;99:2293–352.CrossRefGoogle Scholar
  6. 6.
    Kobayashi H, Brechbiel MW. Nano-sized MRI contrast agents with dendrimer cores. Adv Drug Deliver Rev. 2005;57:2271–86.CrossRefGoogle Scholar
  7. 7.
    Na HB, Song IC, Hyeon T. Inorganic nanoparticles for MRI contrast agents. Adv Mater. 2009;21:2133–48.CrossRefGoogle Scholar
  8. 8.
    Gao JH, Gu HW, Xu B. Multifunctional magnetic nanoparticles: design, synthesis, and biomedical applications. Accounts Chem Res. 2009;42:1097–107.CrossRefGoogle Scholar
  9. 9.
    Gao ZY, Ma TC, Zhao EY, Docter D, Yang WS, Stauber RH, Gao MY. Small is smarter: nano MRI contrast agents—advantages and recent achievements. Small. 2016;12:556–76.CrossRefGoogle Scholar
  10. 10.
    Yoo D, Lee JH, Shin TH, Cheon J. Theranostic magnetic nanoparticles. Acc Chem Res. 2011;44:863–74.CrossRefGoogle Scholar
  11. 11.
    Cheng K, Yang M, Zhang RP, Qin CX, Su XH, Cheng Z. Hybrid nanotrimers for dual T1- and T2-weighted magnetic resonance imaging. ACS Nano. 2014;8:9884–96.CrossRefGoogle Scholar
  12. 12.
    Choi JS, Lee JH, Shin TH, Song HT, Kim EY, Cheon J. Self-confirming, “AND” logic nanoparticles for fault-free MRI. J Am Chem Soc. 2010;132:11015–7.CrossRefGoogle Scholar
  13. 13.
    Im GH, Kim SM, Lee DG, Lee WJ, Lee JH, Lee IS. Fe3O4/MnO hybrid nanocrystals as a dual contrast agent for both T1- and T2-weighted liver MRI. Biomaterials. 2013;34:2069–76.CrossRefGoogle Scholar
  14. 14.
    Shin TH, Choi JS, Yun S, Kim IS, Song HT, Kim Y, Park KI, Cheon J. T1- and T2- dual-mode MRI contrast agent for enhancing accuracy by engineered nanomaterials. ACS Nano. 2014;8:3393–401.CrossRefGoogle Scholar
  15. 15.
    Zhou Z, Huang D, Bao J, Chen Q, Liu G, Chen Z, Chen X, Gao J. A synergistically enhanced T1–T2 dual-modal contrast agent. Adv Mater. 2012;24:6223–8.CrossRefGoogle Scholar
  16. 16.
    Li FF, Zhi DB, Luo YF, Zhang JQ, Nan X, Zhang YJ, Zhou W, Qiu BS, Wen LP, Liang GL. Core/shell Fe3O4/Gd2O3 nanocubes as T1–T2 dual modal MRI contrast agents. Nanoscale. 2016;8:12826–33.CrossRefGoogle Scholar
  17. 17.
    Wang L, Lin H, Ma L, Jin J, Shen T, Wei R, Wang X, Ai H, Chen Z, Gao J. Albumin-based nanoparticles loaded with hydrophobic gadolinium chelates as T1–T2 dual-mode contrast agents for accurate liver tumor imaging. Nanoscale. 2017;9:4516–23.CrossRefGoogle Scholar
  18. 18.
    Yang H, Zhuang YM, Sun Y, Dai AT, Shi XY, Wu DM, Li FY, Hu H, Yang SP. Targeted dual-contrast T1- and T2-weighted magnetic resonance imaging of tumors using multifunctional gadolinium-labeled superparamagnetic iron oxide nanoparticles. Biomaterials. 2011;32:4584–93.CrossRefGoogle Scholar
  19. 19.
    Keasberry NA, Banobre-Lopez M, Wood C, Stasiuk GJ, Gallo J, Long NJ. Tuning the relaxation rates of dual-mode T1/T2 nanoparticle contrast agents: a study into the ideal system. Nanoscale. 2015;7:16119–28.CrossRefGoogle Scholar
  20. 20.
    Guldris N, Argibay B, Kolen’ko YV, Carbo-Argibay E, Sobrino T, Campos F, Salonen LM, Banobre-Lopez M, Castillo J, Rivas J. Influence of the separation procedure on the properties of magnetic nanoparticles: gaining in vitro stability and T1–T2 magnetic resonance imaging performance. J Colloid Interf Sci. 2016;472:229–36.CrossRefGoogle Scholar
  21. 21.
    Lee DE, Koo H, Sun IC, Ryu JH, Kim K, Kwon IC. Multifunctional nanoparticles for multimodal imaging and theragnosis. Chem Soc Rev. 2012;41:2656–72.CrossRefGoogle Scholar
  22. 22.
    Rieffel J, Chitgupi U, Lovell JF. Recent advances in higher-order, multimodal, biomedical imaging agents. Small. 2015;11:4445–61.CrossRefGoogle Scholar
  23. 23.
    Padmanabhan P, Kumar A, Kumar S, Chaudhary RK, Gulyas B. Nanoparticles in practice for molecular-imaging applications: an overview. Acta Biomater. 2016;41:1–16.CrossRefGoogle Scholar
  24. 24.
    Niu DC, Luo XF, Li YS, Liu XH, Wang X, Shi JL. Manganese-loaded dual-mesoporous silica spheres for efficient T1- and T2-weighted dual mode magnetic resonance imaging. ACS Appl Mater Inter. 2013;5:9942–8.CrossRefGoogle Scholar
  25. 25.
    Ganta S, Devalapally H, Shahiwala A, Amiji M. A review of stimuli-responsive nanocarriers for drug and gene delivery. J Control Release. 2008;126:187–204.CrossRefGoogle Scholar
  26. 26.
    Schmaljohann D. Thermo- and pH-responsive polymers in drug delivery. Adv Drug Deliver Rev. 2006;58:1655–70.CrossRefGoogle Scholar
  27. 27.
    Kim KT, Meeuwissen SA, Nolte RJM, van Hest JCM. Smart nanocontainers and nanoreactors. Nanoscale. 2010;2:844–58.CrossRefGoogle Scholar
  28. 28.
    Kanamala M, Wilson WR, Yang MM, Palmer BD, Wu ZM. Mechanisms and biomaterials in pH-responsive tumour targeted drug delivery: a review. Biomaterials. 2016;85:152–67.CrossRefGoogle Scholar
  29. 29.
    Zangabad PS, Karimi M, Mehdizadeh F, Malekzad H, Ghasemi A, Bahrami S, Zare H, Moghoofei M, Hekmatmanesh A, Hamblin MR. Nanocaged platforms: modification, drug delivery and nanotoxicity. Opening synthetic cages to release the tiger. Nanoscale. 2017;9:1356–92.CrossRefGoogle Scholar
  30. 30.
    Park J, An KJ, Hwang YS, Park JG, Noh HJ, Kim JY, Park JH, Hwang NM, Hyeon T. Ultra-large-scale syntheses of monodisperse nanocrystals. Nat Mater. 2004;3:891–5.CrossRefGoogle Scholar
  31. 31.
    Liu ZY, Yi GS, Zhang HT, Ding J, Zhang YW, Xue JM. Monodisperse silica nanoparticles encapsulating up conversion fluorescent and superparamagnetic nanocrystals. Chem Commun. 2008;6:694–6.CrossRefGoogle Scholar
  32. 32.
    Liu JN, Bu JW, Bu WB, Zhang SJ, Pan LM, Fan WP, Chen F, Zhou LP, Peng WJ, Zhao KL, et al. Real-time in vivo quantitative monitoring of drug release by dual-mode magnetic resonance and upconverted luminescence imaging. Angew Chem Int Edit. 2014;53:4551–5.CrossRefGoogle Scholar
  33. 33.
    Li L, Liu C, Zhang LY, Wang TT, Yu H, Wang CG, Su ZM. Multifunctional magnetic-fluorescent eccentric-(concentric-Fe3O4@SiO2)@polyacrylic acid core-shell nanocomposites for cell imaging and pH-responsive drug delivery. Nanoscale. 2013;5:2249–53.CrossRefGoogle Scholar
  34. 34.
    Daly D, Al-Sabi A, Kinsella GK, Nolan K, Dolly JO. Porphyrin derivatives as potent and selective blockers of neuronal Kv1 channels. Chem Commun. 2015;51:1066–9.CrossRefGoogle Scholar
  35. 35.
    Hong J, Xu D, Yu J, Gong P, Ma H, Yao S. Facile synthesis of polymer-enveloped ultrasmall superparamagnetic iron oxide for magnetic resonance imaging. Nanotechnology. 2007;18:135608.CrossRefGoogle Scholar
  36. 36.
    Tang HY, Guo J, Sun Y, Chang BS, Ren QG, Yang WL. Facile synthesis of pH sensitive polymer-coated mesoporous silica nanoparticles and their application in drug delivery. Int J Pharm. 2011;421:388–96.CrossRefGoogle Scholar
  37. 37.
    Brown MA, Semelka RC. MRI: basic principles and applications. 3rd ed. New York: Wiley; 2003. p. 218–21.CrossRefGoogle Scholar
  38. 38.
    Gallo J, Harriss BI, Hernandez-Gil J, Banobre-Lopez M, Long NJ. Probing T1–T2 interactions and their imaging implications through a thermally responsive nanoprobe. Nanoscale. 2017;9:11318–26.CrossRefGoogle Scholar
  39. 39.
    Huang CC, Tsai CY, Sheu HS, Chuang KY, Su CH, Jeng US, Cheng FY, Su CH, Lei HY, Yeh CS. Enhancing transversal relaxation for magnetite nanoparticles in MR imaging using Gd3+-chelated mesoporous silica shells. ACS Nano. 2011;5:3905–16.CrossRefGoogle Scholar
  40. 40.
    Yeh CS, Su CH, Ho WY, Huang CC, Chang JC, Chien YH, Hung ST, Liau MC, Ho HY. Tumor targeting and MR imaging with lipophilic cyanine-mediated near-infrared responsive porous Gd silicate nanoparticles. Biomaterials. 2013;34:5677–88.CrossRefGoogle Scholar
  41. 41.
    Wartenberg N, Fries P, Raccurt O. A gadolinium complex confined in silica nanoparticles as a highly efficient T1/T2 MRI contrast agent. CHEM-EUR J. 2013;19:6980–3.CrossRefGoogle Scholar
  42. 42.
    Brooks RA, Moiny F, Gillis P. On T2-shortening by weakly magnetized particles: the chemical exchange model. Magn Reson Med. 2001;45:1014–20.CrossRefGoogle Scholar
  43. 43.
    Na HB, Lee JH, An K, Park YI, Park M, Lee IS, Nam D-H, Kim ST, Kim S-H, Kim S-W, et al. Development of a T1 contrast agent for magnetic resonance imaging using MnO nanoparticles. Angew Chem Int Edit. 2007;46:5397–401.CrossRefGoogle Scholar
  44. 44.
    Kim T, Momin E, Choi J, Yuan K, Zaidi H, Kim J, Park M, Lee N, McMahon MT, Quinones-Hinojosa A, et al. Mesoporous silica-coated hollow manganese oxide nanoparticles as positive T1 contrast agents for labeling and MRI tracking of adipose-derived mesenchymal stem cells. J Am Chem Soc. 2011;133:2955–61.CrossRefGoogle Scholar
  45. 45.
    Banobre-Lopez M, Garcia-Hevia L, Cerqueira MF, Rivadulla F, Gallo J. Tunable performance of manganese oxide nanostructures as MRI contrast agents. Chem-Eur J. 2018;24:1295–303.CrossRefGoogle Scholar
  46. 46.
    Gallo J, Vasimalai N, Fernandez-Arguelles MT, Banobre-Lopez M. Green synthesis of multimodal ‘OFF–ON’ activatable MRI/optical probes. Dalton Trans. 2016;45:17672–80.CrossRefGoogle Scholar
  47. 47.
    Chen Y, Chen H, Zhang S, Chen F, Sun S, He Q, Ma M, Wang X, Wu H, Zhang LX, et al. Structure-property relationships in manganese oxide—mesoporous silica nanoparticles used for T1-weighted MRI and simultaneous anti-cancer drug delivery. Biomaterials. 2012;33:2388–98.CrossRefGoogle Scholar

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Authors and Affiliations

  1. 1.State Key Laboratory of Magnetic Resonance and Atomic and Molecular Physics, Wuhan Institute of Physics and Mathematics, Chinese Academy of Sciences; Wuhan National Laboratory for OptoelectronicsWuhanChina

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