Effects of PEGylation on the physicochemical properties and in vivo distribution of organic nanotubes
Authors Ding W, Minamikawa H, Kameta N, Shimizu T, Masuda M
Received 9 October 2014
Accepted for publication 13 November 2014
Published 12 December 2014 Volume 2014:9(1) Pages 5811—5823
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 3
Editor who approved publication: Prof. Dr. Thomas J. Webster
Wuxiao Ding, Hiroyuki Minamikawa, Naohiro Kameta, Toshimi Shimizu, Mitsutoshi Masuda
Nanosystem Research Institute, National Institute of Advanced Industrial Science and Technology (AIST), Ibaraki, Japan
Abstract: Application of organic nanotubes (ONTs) into drug nanocarriers ultimately requires validation in live animals. For improving the dispersibility in biological media and in vivo distribution, the outer surface of an ONT was functionalized with polyethylene glycol (PEG) via the coassembly of an ONT-forming lipid with 5–20 mol% of a PEG-tethered lipid analogue (PEG-lipid). Firstly, the effect of PEGylation on the psysicochemical properties of ONTs, such as morphology and dispersibility, was investigated. PEGylation of ONTs slightly reduced the average length and effectively prevented the aggregation in phosphate-buffered saline (PBS). The PEGylated ONTs even showed high thermal stability in aqueous dispersion at least up to 95°C. Secondly, differential scanning calorimetry and powder X-ray diffraction indicated that ~10 mol% of PEG-lipid was completely incorporated into the ONTs, while 20 mol% of PEG-lipid encountered a partial phase separation during coassembly. In the heating differential scanning calorimetry runs, the resultant PEGylated ONTs with 5 mol% PEG-lipid showed no sign of phase separation up to 180°C under lyophilized condition, while those with 10 mol% and 20 mol% PEG-lipid showed some phase separation of the PEG-lipid above 120°C. Finally, PEGylation significantly affected the tissue distribution and prolonged the persistence time in the blood in mice. Non-PEGylated ONTs was quickly cleared from the circulation after intravenous infusion and preferentially accumulated in the lung, while PEGylated ONTs was mainly trapped in the liver and could circulate in the blood up to 24 hours. This study provided valuable information of physicochemical properties and the in vivo distribution behavior of PEGylated ONTs for their potential application into drug nanocarriers.
Keywords: nanostructure, dispersibility, distribution
One-dimensional nanostructures have recently emerged as promising drug nanocarriers at both cell and small animal levels. Carbon nanotube and polymeric nanoparticles with high aspect ratio morphologies enjoyed appreciable advantages in the internalization mechanism and rate into cancer cells,1–3 while flexible polymer rod-like micelles showed much longer blood persistence than spherical counterparts in mice and rats.4 A solid form of lipid self-assemblies, organic nanotubes (ONTs), have also been reported for their applications in the nanomedicine field.5 The large ONT from diacetylenic lipid 1,2-bis(tricosa-10,12-diynoyl)-sn-3-phosphocholine possessed a diameter of 500−1,000 nm and provided the sustained release not only for macromolecular proteins such as transforming growth factor-β, but also for small drugs.6–10 Further functionalization of ONTs offers a selective and efficient drug loading, and controlled release. Some recent studies have demonstrated that incorporating charge and hydrophobicity onto the nanotube inner surfaces leads to encouraging applications for in vitro drug delivery.11–18
A couple of studies of drug-loaded ONTs in animals have also been reported for oral gene delivery,19 intravitreal delivery of anticancer drugs,20 and intravenous delivery of irinotecan.21 An ONT with a length of 2 μm outer diameter of 70–90 nm was found to accumulate specifically in the lung and be quickly cleared from blood circulation.21 Although the observed size of this ONT is less than 100 nm, the carboxyl group-covered hydrophobic surface led this ONT to form large bundles and be poorly dispersed in water. Further, this ONT was biologically unstable because the ONT was decomposed into lipid at a pH of 7.4. In contrast to those poorly dispersed ONTs,21,22 we have successfully developed highly water-dispersed and biologically stable ONTs with an outer diameter less than 20 nm.15,16,23 In our in vitro studies, these ONTs are effective as nanocarriers in terms of high loading for anticancer drugs and proteins and controlled release property, but in vivo validation is indispensable to advance the ONTs into potential drug nanocarriers. We expect that these ONTs having smaller size, higher dispersibility, and higher stability may improve their biodistribution and biological effect.
The modification of polyethylene glycol (PEG) on the surface of nanocarriers, called “PEGylation,” has been widely used to prevent liposomes,24 polymeric nanoparticles,25 and carbon nanotubes26 from premature clearance during circulation in the blood, since the PEGylation improves dispersibility and reduces the uptake by mononuclear phagocyte system. PEGylation of ONT has also been previously reported as a dispersant in preventing the aggregation and in vitro transfection of the ONT-plasmid DNA complex.13 In this work, we further modified the mother ONT (self-assembly of ONT-forming lipid alone) with dual functionalities by a coassembly approach in order to reveal the effect of PEGylation on in vivo distribution. PEG (MW 2000) chain was selectively anchored on the outer surface to provide good dispersibility in physiological condition, and tetraazacyclododecane tetraacetic acid (DOTA) groups on the inner surface for complexation with gadolinium ion for the detection of ONTs (Figure 1). The physicochemical properties of ONTs, such as morphology, dispersibility, and thermal stability were investigated. Finally, the in vivo distribution of the PEGylated ONTs was evaluated by measuring the gadolinium ion, and the existence of PEGylated ONTs in the plasma was also directly visualized by scanning transmission electron microscopic (STEM) observation.
4-(4,6-Dimethoxy-1,3,5-triazin-2-yl)-4-methylmorpholinium chloride (DMT-MM), ethylenediamine, Tri-tert-butyl 1,4,7,10-tetraazacyclododecane-1,4,7,10-tetraacetate (triBoc-DOTA), and trifluoroacetic acid were purchased from the Tokyo Chemical Industry Co, Ltd (Japan), All organic solvents used for the synthesis and coassembly were of analytical grade.
Synthesis of PEG-lipid 2 and DOTA-lipid 3
PEG-tethered lipid analogue (PEG-lipid) 2 was synthesized by the coupling of mono-PEGylated eicosanedioic acid (MW of PEG: 2000)13 with glycyl-glycyl-glycyl-glycine methyl ester15 using DMT-MM as a coupling agent (Figure 2). After 4 hours’ reaction at room temperature, methanol was removed and the residue was redispersed in water for dialysis (MWCO 3,500). The water dispersion was hydrolyzed to remove the methyl group by sodium hydroxide solution, followed by pH adjustment to acidic condition and dialysis to remove sodium chloride. The final dispersion was freeze-dried to get PEG-lipid 2. 1H-NMR (400 MHz, DMSO-d6): δ 7.74–8.02 (m, 4.8 H, -CONHCH2-), 3.75 and 3.83 (d, 8H; -NHCH2CO-), 3.42 (m, 208 H, -OCH2CH2O-), 3.18 (S, 3 H, -OCH3), 2.98 (dd, 2 H, -CONHCH2CH2-), 1.98 (t, 4 H, -CH2CH2CONH-), 1.52 (dd, 2 H, -CONHCH2CH2CH2O-), 1.41 (m, 4 H, -NHCOCH2CH2-), 1.16 (m, 28 H, -CH2-).
Figure 2 Synthesis of (A) PEG-lipid 2 and (B) DOTA-lipid 3.
DOTA-lipid 3: 19-(N-β-D-glucopyranosyl carbamoyl) nonadecanoyl-glycyl-glycyl-glycyl-ethyl ester was synthesized in a similar process as previously reported.15 It was aminolyzed with excess ethylenediamine in dimethyl sulfoxide (DMSO) at 80°C. Addition of methanol gave a precipitation of 19-(N-β-D-glucopyranosyl carbamoyl) nonadecanoyl-glycyl-glycyl-glycyl-ethylamine. Then it was conjugated with triBoc-DOTA using DMT-MM as a coupling agent in DMSO. The DMSO dispersion was freeze-dried and methanol was added to remove excess unreacted 19-(N-β-D-glucopyranosyl carbamoyl) nonadecanoyl-glycyl-glycyl-glycyl-ethylamine by filtration. The filtrate methanol solution was evaporated and water was added to precipitate triBoc-DOTA conjugated lipid. The precipitated solid was filtrated, dried under vacuum, and dissolved in dichloromethane/trifluoroacetic acid to remove the protecting Boc groups. The solution was evaporated to obtain DOTA-lipid 3. 1H-NMR (400 MHz, DMSO-d6): δ 8.04–8.4 (m, 4.9 H, -CONHCH2-), 4.64 (dd, 0.9H; -OCHNHCO-), 3.75 and 3.83 (m, 13 H; -NHCH2CO-, -NCH2CO-), 3.1–3.3 (m, 28 H; H of glucose, -NHCH2CH2NH-), 2.02 (t, 4 H, -CH2CH2CONH-), 1.41 (m, 4 H, -NHCOCH2CH2-), 1.16 (m, 28 H, -CH2-).
Construction of PEGylated ONT and PEGylated DOTA-ONT
PEGylated ONTs were prepared by the coassembly of ONT-forming lipid 1 and PEG-lipid 2 (Figure 1). Sodium salts of 1 and 2 (with 0, 5, 10, and 20 mol% of 2) were first dissolved in 2-propanol-H2O mixed solvent (1/2, v/v) under mild alkaline conditions (pH ~8.5), and the solution was neutralized with dilute hydrochloric acid to a pH around 4.0 to form ONTs. Correspondingly, they were named as mother ONT, 5% PEG-ONT, 10% PEG-ONT, and 20% PEG-ONT, respectively. 2-propanol was removed by evaporation, and the concentration of 1 was adjusted to 5 mg/mL. Morphologies of ONTs were confirmed by the STEM observation, and length distribution was calculated by counting ~100 nanotubes in the STEM images. Self-assembly of 2 was prepared by the similar pH adjustment in water. The NaCl in the mother ONT dispersion was removed by membrane filtration and the mother ONT was redispersed in water.
DOTA-ONT was prepared by the same method using 1 and 3, while PEGylated DOTA-ONT was formulated with 1, 2, and 3. Self-assembly of 3 was prepared by the similar pH adjustment in water. Ten mol% 2 and 10 mol% 3 were mixed with lipid 1. Any free lipid 3 was removed by dialysis (MWCO 12,000) since it is soluble in water under pH 4.0. The final nanotube dispersion was concentrated to 5 mg/mL of 1, and the pH was adjusted within 6.5~7 for the complexation with gadolinium (III) acetate (0.9 equivalent of 3) on the ONT inner surfaces. The gadolinium (III) concentration was about 0.584 μmol/mL as measured by inductively coupled plasma-atomic emission spectroscopy (ICP-AES, Horiba Ultima). Dispersibility and size of those ONTs with DOTA ligands were essentially the same with corresponding counterparts without DOTA ligands. For brevity in the following text, DOTA-ONT and PEGylated DOTA-ONT refer to the gadolinium-labeled ONTs.
Differential scanning calorimetry and powder X-ray diffraction analysis of ONTs and self-assembly of 2
About 20 mg of freeze-dried ONTs or self-assembly of 2 was hermetically sealed into a silver capsule and the differential scanning calorimetry (DSC) curves were recorded at a heating rate of 2°C/minute. The X-ray diffraction (XRD) patterns of 10% PEG-ONT and self-assembly of 2 were measured with a Rigaku Type 4037 diffractometer using graded d-space elliptical side-by-side multilayer optics, monochromated Cu-Kα radiation (40 kV, 30 mA), and an imaging plate (R-Axis IV). The exposure time was 30 minutes with a 150 nm sample-to-camera length. The temperature of XRD samples was controlled to room temperature and 170°C with a Mettler Toledo FP92 hotstage.
The size change of ONTs in deionized water and phosphate-buffered saline (PBS, pH 7.4) was evaluated by the dynamic light scattering (DLS) method (Malvern Zetasizer Nano). To study the thermal stability of ONT dispersions, 1 mL of 10% PEG-ONT dispersion was put into two glass vials; one was kept at room temperature, and the other was treated in an oil bath (95°C) for 5 minutes. After cooling to room temperature, 10× PBS (0.1 mL) was added into the dispersion samples and the turbidity was recorded on a Hitachi U-3900H UV-Vis spectrometer. The mother ONT was used as a negative control.
In vivo distribution of DOTA-ONT and PEGylated DOTA-ONT
The animal experiments were performed with the approval of the life science division of AIST. Each group used four to five mice with an average body weight of 27 g. Injected dose of gadolinium is about 4.33 μmol/kg for both ONTs. Since the quick intravenous injection of DOTA-ONT (200 μL, 5 mg/mL of the 1) resulted in the instant death of the mice, it was diluted into 1 mg/mL for slow intravenous infusion into mice. Nevertheless, infusion of DOTA-ONT still resulted in a poor physical condition of mice, and many died after 1 hour. Therefore, the distribution of DOTA-ONT was only investigated at 1 hour. The PEGylated DOTA-ONT (200 μL, 5 mg/mL of the 1) was quickly injected into mice and distribution was studied until 24 hours. Blood samples (~0.8 mL) were taken from the portal vein and the mice were sacrificed at 1, 6, and 24 hours after injection. Lung, liver, kidney, and spleen were removed, rinsed in saline, and weighed for digestion. Blood samples (0.5 mL) were digested by 2 mL of HNO3, and the mixture was evaporated to dryness at 100°C with an electric hot plate. Finally, 10 mL of HNO3 solution (1 M) was added to dissolve the solid. These whole organs were cut into small pieces and digested by mixed acid of HNO3–HClO4 (4:1, v:v) for 48 hours at room temperature, and then evaporated to dryness at 100°C on an electric hot plate. Finally, 10 mL of HNO3 solution (1 M) was added to dissolve the solid. These solutions were allowed to settle at room temperature for 2 days, and the gadolinium concentration in the clear supernatant was measured by ICP-AES (detected at 342.246 nm). The blood volume was set as 0.0778 mL/g body weight to calculate the whole amount of gadolinium in the blood.27
For the direct visualization of PEGylated DOTA-ONT in the plasma, blood samples were collected at 5 minutes, 1 hour, 6 hours, and 24 hours and were centrifuged at 3,500 rpm to get the plasma. Ten microliters of plasma samples were diluted into 1 mL water containing 10 μL of staining agent 2% phosphotungstate solution. Two microliters of the diluted samples were uniformly dried on a carbon grid for STEM observation. The ONT numbers in the typical STEM images partially reflected the ONT concentration in the blood.
Results and discussion
Morphologies of ONTs and self-assemblies from 2 and 3
The mother ONT and PEGylated ONTs had uniform tubular morphologies and similar outer diameters of 16–18 nm except the 20% PEG-ONT (Figure 3A–D). By contrast, lipid 2 self-assembled into irregular nanostructures (Figure 3E). Such irregular nanostructures were essentially not found in the STEM images of PEGylated ONTs. The mother ONT, 5% PEG-ONT, and 10% PEG-ONT showed fine tubular morphologies with regular open ends (Figure 2A–C), while 20% PEG-ONT produced many broken nanotube fragments and a minor amount of large tubes (40 nm outer diameter, arrow marks in Figure 3D). The STEM result suggested that, at 20 mol% of PEG-lipid 2, phase separation of 2 or coexistence of other assemblies might have occurred during the coassembly process. The DOTA-lipid 3 was designed to selectively anchor on the inner surfaces of DOTA-ONT and PEGylated DOTA-ONT. At pH 4.5, DOTA-lipid 3 self-assembled into fine nanofibers with a size between 3.0 and 6.0 nm (Figure 3F and Figure S1). Ten mol% of 3 seemed to have coassembled into DOTA-ONT and PEGylated DOTA-ONT, since they showed fine tubular morphologies and such nanofibers were not found in the STEM images (Figure 3G and H). The dispersibility and size of DOTA-modified ONTs were essentially the same with corresponding counterparts without DOTA ligands.
PEGylation affected the length distribution of ONTs. The mother ONT showed a major length distribution between 400 and 600 nm (Figure 4). The ONT modified with 5 mol% of 2 did not show a large difference in length distribution from the mother ONT, while those with 10 mol% and 20 mol% of 2 became shorter in the length range of 200 to 400 nm. These effects on morphology and length suggested that the bulky and hydrophilic PEG chain might perturb the intermolecular association or the molecular arrangement between lipids at a high fraction of 2.
Figure 4 Length distribution of mother ONTs and PEGylated ONTs.
Dispersibility and thermal stability of ONTs in PBS buffer
DLS measurement revealed the PEGylation dramatically improves the dispersibility of ONTs in PBS buffer. The dispersibility of ONTs in deionized water and PBS were investigated by DLS measurement at room temperature. Although the measured mean size (Figure 5) did not precisely reflect the length of ONTs (Figure 4), it could definitely reflect the aggregated/dispersed status. Figure 5 clearly showed that the mother ONT aggregated in PBS (pH 7.4) with the increase of average size from 180 nm to more than 10 μm, while the PEGylated ONTs stayed between 120 and 160 nm in PBS. Good dispersibility of mother ONT in water may be attributable to the repulsive surface charge arising from an excess adsorption of hydroxyl ions (OH−) onto the surface as reported previously.28 In the buffer solutions, the increased ions may shield the surface charge, and cause the aggregation of the nanotubes. On the other hand, the PEGylated ONTs still had the steric repulsion of the PEG chain to keep the nanotubes well dispersed even in the buffers. This dispersibility experiment also suggested that 2 was effectively anchored onto the outer surface of PEGylated ONTs. Similarly to the phenomenon in PBS, the mother ONT also formed agglomeration in mouse plasma (Figure S2), while the PEGylated ONTs effectively prevented the agglomeration in both PBS and plasma.
Figure 5 Mean particle size of ONTs in water and PBS as measured by DLS.
Further, 10% PEG-ONT was stable enough to retain the PEG chain on its outer surface even at 95°C in water. Dissociation of PEG-conjugated lipid from self-assembled vehicles was commonly observed over the gel–liquid crystal phase transition temperatures or under dilute conditions.29 Toward practical applications, the retention of PEG-lipid on ONTs is an important physicochemical property regarding the storage and heat sterilization of PEGylated ONTs. Ten percent PEG-ONT dispersion was selected because of its high fraction of 2 and fine tubular morphology. The transmittance of the heat-treated 10% PEG-ONT dispersion in PBS buffer was exactly the same as the nontreated one (Figure 6). Since the complete dissociation of 2 from 10% PEG-ONT would result in an aggregation in PBS, this result suggested that the coassembled 2 was stably anchored on ONT even at 95°C in aqueous dispersion, offering a possibility for the long-term storage and heat sterilization of the PEGylated ONTs. At a lower fraction of 2, 5% PEG-ONT was most likely to have the same thermal stability.
Figure 6 Transmittance of 10% PEG-ONT and mother ONT dispersions in PBS buffer at room temperature.
DSC and XRD analysis
The coassembled status and maximum amount of 2 in ONTs were analyzed by DSC analysis, which has been widely employed for studying the phase behavior of liposome formulations.30,31 The DSC results showed that up to 10 mol% of 2 was completely coassembled into the ONTs without phase separation. In the DSC measurement (Figure 7, Table S1), the mother ONT showed good thermal stability since no endothermic or exothermic peaks were found below 180°C. The high thermal stability of ONT may be attributed to the thermally stable solid structure due to the strong intermolecular interactions (hydrogen bonding and hydrophobic interaction). By contrast, self-assembly of 2 showed two pronounced peaks with peak values of 53°C and 103°C, of which the endothermic peak at 53°C was associated with the melting of PEG chain.32 Five percent and 10% PEG-ONT did not show such endothermic peaks at the lower temperature region, while 20% PEG-ONT showed a small but evident endothermic peak at 37°C corresponding to the melting of PEG chain. This result suggested that, during the coassembly process, phase separation of 2 from ONTs did not occur at 5 mol% and 10 mol% of PEG-lipid 2, while some phase separation occurred at a high PEG-lipid 2 content (~20 mol%) and might contribute to the formation of larger tubes (indicated by the arrows in Figure 3D). It was reported that the maximum composition of PEG2000-phospholipid incorporated into liposomes was about 7.5 mol%.30,33
Figure 7 DSC curves of ONTs and self-assembly of 2.
Pronounced exothermic phase transition was found for 10% PEG-ONT at 148°C and 20% PEG-ONT at 129°C. They were plausibly due to the heat-induced phase separation, such as detachment of 2 from ONTs for the following reasons: (1) The polarized optical microscopy indicated that the phase transition of 10% PEG-ONT was a solid-to-solid type, while that of self-assembly of 2 was a solid-to-liquid one (Figure S3). (2) The transition occurred only on the first heating (Figure S4). (3) After the transition, 10% PEG-ONT lost its high dispersive nature in PBS buffer but retained tubular structure (Figure S5). (4) The sharp diffraction peak of PEG2000 chain in 10% PEG-ONT almost disappeared after heating as described in the coming XRD analysis. Although the reason why the transition became exothermic was unclear, the possible detachment of 2 might induce subsequent rearrangement into a highly ordered molecular packing within the nanotubes, leading to an exothermic event.
To clarify the molecular packing of PEGylated ONTs and confirm the phenomenon of heat-induced phase separation, lyophilized 10% PEG-ONT and self-assembly of 2 were examined by XRD analysis (Figure 8). Ten percent PEG-ONT showed three diffraction peaks with d-spacing values of 7.1 nm, 4.2 nm, and 3.3 nm (a weak shoulder), while self-assembly of 2 only gave a broad peak around 5.5 nm. Compared to the previously reported mother ONT showing a single d-spacing of 4.02 nm;15 the main d-spacing peak of 4.2 nm and shoulder peak of 3.3 nm were assigned to the two tilt patterns of 1 in 10% PEG-ONT. A different preparation method probably induced the slight difference of molecular arrangement in the nanotube, since the previous ONT was prepared by cooling of hot DMSO solution and the latter PEGylated ONTs by pH adjustment method in 2-propanol-H2O solution.
It is remarkable that the sharp peak of 7.1 nm was only found in the 10% PEG-ONT. Such a large d-spacing value might indicate the large PEG2000 chain coil is exposed onto the outer surface, although we did not observe the PEG chains on electron microscopy. To some extent, this speculation was supported from the thickness of PEG2000 layer observed on liposomes. Based on small angle X-ray scattering study, the thickness of the PEG2000 layer on liposomes was estimated to be ~5 nm when the PEG2000 fraction is 10 mol%.34 The self-assembly of 2 gave a broad peak with d-spacing of 5.5 nm as measured by the present powder XRD analysis. The difference in thickness of each PEG moiety was attributable to difference in density of PEGylation and morphology, which may cause deformation of random coils of PEG.
When the temperature of 10% PEG-ONT was raised to 170°C, which is beyond the exothermic peak (148°C), the d-spacings of 1 (4.2, 3.3 nm) were essentially unchanged. Obvious change was found for the d-spacing of the PEG2000 chain; the sharp peak of 7.1 nm almost disappeared into a small shoulder peak similar to that of self-assembly of 2. These results suggested that, during the transition, PEG-lipid 2 might dissociate from the ONTs, and subsequent rearrangement of 1 probably induced the exothermic transition peaks. Unlike 10% and 20% PEG-ONT, the mother ONT and 5% PEG-ONT did not show such phase separation at least up to 180°C, indicating that the high fraction of PEGylation decreased the thermal stability of ONTs.
In conclusion, PEG-lipid 2 was completely incorporated into ONTs until a fraction of 10 mol%, and the 10% PEG-ONT showed excellent thermal stability both in aqueous dispersion and dehydrate conditions. In the dehydrated condition, a heat-induced phase separation of 2 from dry PEGylated ONTs was observed above 120°C on the first heating cycle.
In vivo distribution
Formulations containing DOTA-gadolinium complex have been widely employed as MRI contrast agents as well as tracers for the in vivo quantification of drug nanocarriers.27,35,36 In this study, 10 mol% of DOTA-lipid 3 was coassembled with 1 and 2 and the ONTs were labeled with gadolinium(III) acetate (0.9 equivalent to 3) for the in vivo quantitative detection of ONTs by ICP-AES. Since dialysis treatment has removed any free 3, gadolinium ions should specifically complex with the ONTs on the inner surface. After the addition of 0.9 equivalent gadolinium(III) acetate into ONTs, the mixture was again subjected to dialysis to check the existence of any free gadolinium ions. The gadolinium ions in the dialysis solution were below the detection limit. This result suggested the successful coassembly of 3 into ONTs and labeling of ONTs with gadolinium. The concentration of gadolinium in the ONTs was about 0.584 μmol/mL, and the injected dose of gadolinium is calculated as 4.33 μmol/kg for each mouse. Such a dose might be too low to visualize the distribution of ONTs in all the subject organs by MRI. MRI contrast agents, such as liposomes and micelles, usually require high doses of gadolinium (such as higher than 30 μmol/kg) to generate enough signal-to-noise ratio.27,37,38 Therefore, the alternative method ICP-AES was employed for qualifying the amount of ONTs in mouse tissues.
The PEGylation significantly affected the tissue distribution of ONTs and improved the persistence time in the blood circulation in mice (Figure 9). For DOTA-ONT at 1 hour after infusion, about 66% of injected dose was accumulated in the lung, 25% in the liver, and less than 5% in the blood. In contrast, highly dispersed PEGylated DOTA-ONT remarkably reduced the accumulation in the lung, increased the accumulation in the liver, and remarkably prolonged the circulation time in the blood. At 1 hour postinjection, about 30% of injected PEGylated DOTA-ONT remained in the blood. The amount in the blood was dropped to about 10% and less than 5% at 6 hours and 24 hours, respectively. The result of DOTA-ONT was quite similar to the lung accumulation of aforementioned poorly dispersed ONT, in which the high axial ratio morphology of ONT was accounted as one of the factors in the high lung accumulation.21 Drug nanocarriers larger than 6 μm were widely acknowledged to be easily trapped by the lung capillaries via intravenous injection.39,40 By the same mechanism, DOTA-ONT specifically accumulated in the lung because of its agglomeration and size increase in the blood (Figure S2). We would like to point out that such event was mainly responsible for the suffocation and instant death of mice after intravenous injection of DOTA-ONT. PEGylated DOTA-ONT avoided the accumulation in the lung simply due to its high dispersibility in biological medium, small size, and short length. In other words, PEGylation could also alleviate the acute toxicity of ONTs via intravenous injection.
Figure 9 Distribution of DOTA-ONT and PEGylated DOTA-ONT in mice.
Although PEGylated DOTA-ONT prolonged the circulation time in the blood, it still accumulated in the mouse liver; the persistence time was much like those of PEGylated carbon nanotubes, and they were much shorter than the polymeric filaments.4 A couple of studies reported that PEGylated carbon nanotubes also showed a circulation less than 24 hours.26,41 Although the Young’s modulus for polymeric filaments was not reported, self-assembled ONTs (Young’s modulus E ~720 MPa) and carbon nanotubes (E ~106 MPa) were considered to have more high rigidness than the flexible filaments.42,43 Further, present PEGylated DOTA-ONT showed a mean length between 200 and 400 nm, which may be too short to show “shape effect” as found in the long polymeric filaments (length is several micrometers). We suggest the high rigidness and short length are the main reasons for the lack of “shape effect” and its short blood persistence time in mice. Since long PEGylated ONT (in micrometer order) was difficult to prepare by the pH-induced coassembly process, the effect of the aspect ratio on the in vivo distribution was not investigated.
Due to its biological stability and high aspect ratio, the existence of PEGylated ONT in the plasma was further visible under STEM observation (Figure 10). Many nanotubes were found in the plasma at 5 minutes after injection. The number of nanotubes decreased at 1 hour and 6 hours, and nanotubes seemed to be completely cleared from the blood after 24 hours. The direct visual STEM observation was quite coincide with the quantitative measurement of gadolinium by ICP-AES.
We successfully prepared PEGylated ONTs by a coassembly approach, and up to 10 mol% PEG-lipid could be completely incorporated into ONTs. The PEGylation effectively prevented the aggregation of the ONTs in biological mediums. Because of the strong intermolecular interactions, heat-induced phase separation of PEG-lipid from dry PEGylated ONT was observed only when the temperature was higher than 120°C, and no phase separation was observed for the 10% PEG-ONT dispersion under 95°C. Compared to the non-PEGylated ONT, the PEGylation remarkably decreases the accumulation of ONTs into the lung and improved the blood persistence time up to 24 hours in mice. Therefore, the PEGylated ONT holds promise as a novel drug nanocarrier because of its thermal stability and improved blood circulation.
The manuscript was written through contributions of all authors. All authors have given approval to the final version of the manuscript.
The authors report no conflicts of interest in this work.
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Figure S1 pH-dependent self-assembly of DOTA-lipid 3.
Figure S2 Agglomeration of mother ONT in mouse plasma.
Table S1 The exothermic temperatures and enthalpies of PEGylated ONTs and self-assembly of 2 based on DSC measurement
Figure S4 DSC cycles of dry 10% PEG-ONT.
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