Nanoscale Metal\xe2\x80\x93Organic Frameworks for Biomedical Imaging and Drug Delivery
CONSPECTUS Metal\xe2\x80\x93organic frameworks (MOFs), a class of hybrid materials formed by the self-assembly of polydentate bridging ligands and metal-connecting points, have been studied for a variety of applications. Recently, these materials have been scaled down to nanometer sizes, and this Account details the development of nanoscale metal\xe2\x80\x93organic frameworks (NMOFs) for biomedical applications. NMOFs possess several potential advantages over conventional nanomedicines such as their structural and chemical diversity, their high loading capacity, and their intrinsic biodegradability. Under relatively mild conditions, NMOFs can be obtained as either crystalline or amorphous materials. The particle composition, size, and morphology can be easily tuned to optimize the final particle properties. Researchers have employed two general strategies to deliver active agents using NMOFs: by incorporating active agents into the frameworks or by loading active agents into the pores and channels of the NMOFs. The modification of NMOF surfaces with either silica coatings or organic polymers improves NMOF stability, fine-tunes their properties, and imparts additional functionality. Preliminary biomedical applications of NMOFs have focused on their use as delivery vehicles for imaging contrast agents and molecular therapeutics. Because NMOFs can carry large amounts of paramagnetic metal ions, they have been extensively explored as magnetic resonance imaging (MRI) contrast agents. Both Gd3+- and Mn2+-containing NMOFs have shown excellent efficacy as T1-weighted contrast agents with large per metal- and per particle-based MR relaxivities. Fe3+-containing NMOFs have demonstrated excellent T2-weighted contrast enhancement. Upon intravenous injection of iron carboxylate NMOFs in Wistar rats, researchers observed negative signal enhancement in the liver and spleen, which dissipated over time, indicating the degradation and clearance of the NMOF. Through the incorporation of luminescent or high Z element building blocks, NMOFs have also served as viable contrast agents for optical imaging or X-ray computed tomography (CT) imaging. Incorporation of membrane impermeable dyes into NMOFs allowed for their uptake by cancer cells and for their controlled release as the framework decomposed. NMOFs have been used to deliver anticancer drugs and other chemotherapeutics. Cisplatin prodrugs were incorporated within NMOFs at exceptionally high levels, either through use of the prodrug as the building block or through attachment of the prodrug onto the framework after synthesis. These NMOFs were encapsulated within a silica shell and targeted to cancer cells. In vitro assays revealed that the targeted NMOFs possessed similar efficacy to cisplatin, while the nontargeted NMOFs were less active. Several different therapeutic molecules were loaded within porous iron-carboxylate NMOFs at unprecedented levels. The NMOF showed sustained drug release with no burst effect, and in vitro assays revealed that the nanoencapsulated drug possessed similar efficacy to the free drug. Although still at a very early stage of development, NMOFs have already shown great promise as a novel platform for nanomedicine. The compositional tunability and mild synthetic conditions used to produce NMOFs should allow for the incorporation of other imaging and therapeutic agents and their effective delivery to targeted cells in vivo.
Introduction<!>Synthesis of Nanoscale Metal\xe2\x80\x93Organic Frameworks<!>Strategies to Incorporate Biomedically Relevant Agents within NMOFs<!>Surface Modification of NMOFs<!>Magnetic Resonance Imaging<!>Optical Imaging<!>X-ray Computed Tomography (CT) Imaging<!>Drug Delivery<!>Conclusions and Future Outlook
<p>Metal–organic frameworks (MOFs), also called coordination polymers or coordination networks, are a class of hybrid materials formed by the self-assembly of metal ions or clusters and polydentate bridging ligands typically under mild conditions. Due to virtually limitless combinations of metals and ligands, the physicochemical properties of MOFs can be judiciously tuned for specific applications. As a result, bulk phase MOFs have shown promise for a number of diverse applications including gas storage,1,2 catalysis,3–5 nonlinear optics,6 separations,7,8 sensing,9,10 and light-harvesting.11 Because MOFs can exhibit exceptionally high surface areas with large pore sizes, they have also been investigated for applications in loading and controlled release of several drug molecules.12–14 However, MOFs need to be scaled down to the nanoregime to form nanoscale metal–organic frameworks (NMOFs) for use as delivery vehicles for imaging agents and drug molecules. We and others have recently shown that NMOFs can be synthesized using a variety of different techniques that have been developed for inorganic and organic polymeric nanoparticles. NMOFs not only maintain the structural diversity and physicochemical properties as bulk MOFs but also exhibit particle dimensions in the tens to hundreds of nanometers range, making them potential nanocarriers for imaging agents and drug molecules.15–17</p><p>Although a large number of materials have been developed as nanocarriers for imaging and therapuetic agents,18–21 the majority of them can be categorized into either purely inorganic (such as quantum dots, Fe3O4, and Au nanoparticles) or purely organic (such as liposomes, dendrimers, polymers). Each of these classes of nanomaterials has its own strengths and weaknesses. NMOFs possess some potential advantages over existing nanocarriers. First, MOFs are compositionally and structurally diverse, allowing for the facile synthesis of NMOFs of different compositions, shapes, sizes, and chemical properties. Second, NMOFs are intrinsically biodegradable as a result of relatively labile metal–ligand bonds, making it possible to rapidly degrade and clear the nanocarriers after the intended task is completed. In this Account, we intend to summarize recent advances in the development of NMOFs as delivery vehicles for imaging agents and molecular therapeutics. More specialized reviews focusing on the synthesis of NMOFs15,16 and the use of NMOFs in biomedical imaging22 and in drug delivery23 have recently appeared.</p><!><p>As the synthesis of nanoscale and microscale MOFs has recently been reviewed,15,16 we only outline general synthetic strategies here with specific examples of the synthesis of biomedically relevant NMOFs. Four general methods have been utilized to synthesize NMOFs: nanoprecipitation, solvothermal, reverse microemulsion, and surfactant-templated solvothermal reactions. The first method tends to yield amorphous materials, while the latter three methods can afford crystalline materials, owing to the ability to exert a better control on nanoparticle nucleation and growth kinetics. The first two methods are surfactant-free, whereas the last two methods rely on surfactants not only to control the particle synthesis but also to stabilize these particles.</p><p>In a typical NMOF synthesis, precursor solutions are mixed together to allow particle nucleation and growth (Figure 1a). In the nanoprecipitation method, nanoparticles form because the particles are insoluble in the solvent system whereas the individual precursors remain soluble. This strategy was used to synthesize NMOFs composed of the anticancer prodrug c,c,t-Pt(NH3)2Cl2(succinate)2 (DSCP) and Tb3+ (1).24 In this synthesis, the pH value of an aqueous solution of TbCl3 and [NMeH3]2DSCP was adjusted to 5.5 with aqueous sodium hydroxide. Methanol was then quickly added to the precursor solution, leading to the instantaneous formation of 1 which were shown by SEM and DLS to adopt a spherical morphology with a diameter of 50–60 nm (Figure 1b). 1 contains 75 wt % of the DSCP prodrug; such a high loading of cisplatin has not been achieved using other nanocarriers.26,27</p><p>Solvothermal synthesis of NMOFs can be achieved with either conventional heating or a microwave. Because high reaction temperatures are involved in the solvothermal method, more extensive transformations of the precursors typically occur before the formation of the NMOF nanoparticles. Temperatures and heating rates provide additional parameters to control the NMOF particle nucleation and growth. For example, Fe3+ NMOF particles with the formula of Fe3(μ3-O)Cl(H2O)(BDC)3 (2) were synthesized by heating an equimolar solution of FeCl3 and terephthalic acid (BDC) with a microwave.25
2 displayed an octahedral morphology with an average diameter of 200 nm (Figure 1c). PXRD studies showed that 2 was highly crystalline and adopted the known MIL-101 structure. 2 could also be modified by incorporating a fraction of 2-aminoterephallic acid (NH2–BDC) to form 2a particles that provided an orthogonal amino group for further functionalization. 2a retained the MIL-101 structure with up to 17.5 mol % of NH2–BDC incorporation, while the particles synthesized with higher amounts of NH2–BDC adopted the nonporous MIL-88B structure.</p><p>Surfactant-assisted synthesis of NMOFs can be carried out at room temperature or at elevated temperatures. Because the building blocks for NMOFs are typically water-soluble, reverse microemulsions provide another method to control the nucleation and growth kinetics of NMOF particles. Reverse microemulsions are formed by using surfactants to stabilize water droplets within a nonpolar organic phase (Figure 2a). This method was used to synthesize crystalline Gd(BDC)1.5(H2O)2 (3) nanorods (Figure 2b).28 Two separate microemulsions containing either GdCl3 or [NMeH3]2[BDC] were mixed and allowed to react for a given amount of time. The particle morphologies could be controlled by adjusting the w value (water to surfactant molar ratio) of the micro-emulsion. 3 synthesized at w = 10 was 1–2 μm in length and 100 nm in diameter. Nanorods of 100–125 nm in length and 40 nm in diameter were obtained when the w value was decreased to 5. Gd(BTC)(H2O)3 (4, BTC = benzene-1,2,4-tricarboxylate) nanoplates of ~100 nm in diameter and ~ 35 nm in thickness were also synthesized by this method. Both 3 and 4 were crystalline and matched known lanthanide-carboxylate bulk phases.</p><p>Surfactant molecules can also be used to template the NMOF synthesis under solvothermal conditions (Figure 2a) by coating the surfaces of growing NMOF particles. Surfactant molecules play an important role in defining NMOF morphologies. For example, Gd-BHC NMOFs (BHC = benzene hexacarboxylic acid) were synthesized by a surfactant templated solvothermal method.29 A reverse microemulsion of GdCl3 and [NMeH3]6[BHC] was transferred to a Parr reactor and heated at 120 °C. The resulting NMOF had the formula Gd2(BHC)(H2O)6 (5) and exhibited a blocklike morphology with dimensions of 25 × 50 × 100 nm3 (Figure 2c). 5 was crystalline and matched a previously reported lanthanide-BHC phase. The compositions and morphologies of Gd-BHC NMOFs were also shown to be sensitive to the pH values of the reaction system. MOF microparticles of a different composition were obtained when the reaction was carried out at lower pH.29</p><p>The four general methods described above have been adopted to synthesize a large number of NMOFs. With the ability to independently adjust NMOF precursors, reaction solvents, pH values, temperatures, surfactant or other templating molecules, w values, and other parameters, a range of NMOFs with well-defined compositions and morphologies have been synthesized. It has also been shown that surface termination can be an important parameter in defining NMOF morphologies.30,31 Although the synthesis of NMOFs has been phenomenologically described, there is little study on the NMOF growth mechanism and kinetics. Fundamental understanding of NMOF growth mechanism and kinetics will facilitate the development of NMOFs as a promising class of hybrid nanomaterials for biological and biomedical applications.</p><!><p>Several different methods have been developed to incorporate imaging and therapeutic agents into NMOFs by taking advantage of the tailorability of NMOFs to afford very high agent loadings. These loading methods fall into two general categories: direct incorporation during NMOF synthesis or postsynthesis loading (Figure 3). A combination of these two strategies can also be used to load different agents into NMOFs to allow the development of multimodal imaging agents or theranostic nanoparticles.</p><p>In the direct incorporation strategy, biomedically relevant agents are used as either the metal connecting points28–30,32 or the bridging ligand to assemble NMOFs (Figure 3a).24,33,34 Paramagnetic metal ions such as Gd3+, Fe3+, and Mn2+ not only link the ligands to form the NMOFs but also act as magnetic resonance imaging (MRI) contrast enhancement agents either in intact NMOF particles or upon dissolution of NMOF particles (Table 1). DSCP and I4–BDC were used to bridge metal centers to form NMOFs to provide the anticancer therapeutic cisplatin or the high Z element iodine for CT imaging, respectively.24,33 The direct incorporation strategy has the ability to achieve very high agent loadings with uniform distribution throughout the nanoparticle, but the morphology and physicochemical properties of these NMOFs need to be individually tuned. Care must also be taken to ensure that the agent is not altered or degraded during the NMOF synthesis. The direct incorporation strategy can be modified to include a small amount of the biomedically relevant agent during the synthesis as a dopant, imparting additional functionality to the NMOF (Table 1). This method has been used to encapsulate a number of different agents with various properties such as optical dyes, chemotherapeutics, proteins, and smaller nanoparticles.35–41 However, only a low drug loading can be achieved by this method and the release kinetics of the agent from the NMOF may be very different than the framework decomposition rate.</p><p>In the postsynthesis loading strategy, biomedically relevant agents are loaded into the NMOF pores. After the synthesis of highly porous NMOFs, the active agent is incorporated within the NMOF by noncovalent (Figure 3b1) or covalent interactions (Figure 3b2). Noncovalent drug loading was first demonstrated using bulk phase MOFs,12–14 achieving impressive loading of up to 1.4 g of ibuprofen/g of MOF.12 Release studies showed very slow, sustained drug release from the framework with minimal burst effects. More recent studies have extended this strategy to NMOFs which have been loaded with hydrophilic, amphiphillic, and hydrophobic drugs.30 The NMOF pore size must be larger than the encapsulated agent to afford high loadings.</p><p>Since noncovalent drug loading is an inherently reversible process, subsequent processing of the NMOF may lead to premature release of the agent. Postsynthesis covalent attachment of the agent offers a more robust approach, as the agent will only be released when the NMOF decomposes. In this method, orthogonal functional groups within the frameworks of porous NMOFs are used to covalently attach active agents.25,42 This strategy effectively creates a prodrug, so it is essential that the functionality of the agent is maintained. The active drug must be cleavable from the NMOF under specific biological conditions. As functional groups at or near the surface of the nanoparticle are kinetically more accessible, agent loading might not be uniform throughout the NMOF particles. As an example, NMOF 2a possessed NH2–BDC groups, which were used to attach either an optical contrast agent or a chemotherapeutic through covalent bonds.25</p><!><p>As-synthesized nanomaterials typically need to be further functionalized to optimize their in vivo performance. Surface modification is a commonly used strategy for improving water dispersity, reducing plasma protein binding, avoiding the reticuloendothelial system, and adding affinity molecules to target specific cells or tissues.43 Surface modification is particularly important for NMOFs because of the intrinsic instability of many NMOFs under physiological conditions; surface coatings can slow down the degradation of NMOFs and thus prevent premature release of cargoes. Two general strategies have been used to modify the NMOF surfaces: silica encapsulation and coating with organic polymers (Figure 4). Other surface functionalization approaches need to be explored to further optimize the in vivo performance of many NMOFs.</p><p>Lin and co-workers first stabilized NMOFs by encapsulating them within a silica shell. Silica coatings have been extensively used to modify inorganic and polymer nanoparticles.44,45 A silica shell offers several advantages as a surface coating, including biocompatibility, increased water dispersibility, and easy functionalization with silyl-derived molecules. Generally, NMOFs are first coated with a hydrophilic polymer, such as polyvinylpyrrolidone (PVP), to keep the NMOF particles well dispersed so that individual NMOF particles (but not aggregates) are coated with silica shells. For example, NMOF 3 was first coated with PVP and then treated with tetraethylorthosilicate (TEOS) in basic ethanol to afford 3@silica core–shell nanostrcutures.46 The silica shell thickness can be controlled by adjusting the reaction time or reactant concentrations. Release profile experiments demonstrated that a silica shell significantly slows down the rate of NMOF dissolution and Gd release, and the kinetics of Gd3+ release depends on the silica shell thickness. This method was also used to coat Tb3+- and Mn2+-carboxylate NMOFs.24,32
2a was coated with silica by an alternative method using sodium silicate as the silica source as iron-carboxylate NMOFs are unstable under basic conditions.25 The surface of these core–shell NMOFs can be further modified by grafting a silyl-derived molecule onto the silica shell through surface silanol groups to impart additional functionality.24,25,32,46 For example, RGD-targeted 1 increased its anticancer efficacy against human colon cancer cells compared to the untargeted 1.24</p><p>Subsequent studies have modified the surface of NMOFs with organic polymers (Figure 4) as a way to enhance biocompatibility and retard framework decomposition.30,47–49 The polymers must possess an end group that can bind to the NMOF through either vacant metal coordination sites, electrostatic attraction to the particle surface, or covalent attachment to the bridging ligand. Polymers can be added either during NMOF synthesis or postsynthetically. A number of different polymers were conjugated to 3 through the thiol end groups of the polymers which bind to vacant Gd3+ coordination sites.47,48 The polymer coatings slow down the release of Gd3+ ions. Additional functional groups on the polymer allowed for the incorporation of chemotherapeutics, optical imaging agents, and targeting agents. Polymer modification also altered the properties of 3 as a MRI contrast agent. Lin and co-workers modified the surface of several NMOFs with PVP to stabilize the NMOF and increase its dispersibility as a way to increase the efficiency of a subsequent silica coating step.24,32,46 As a large inventory of polymers are available for biomedical applications, surface modification with polymers imparts additional tunability to optimize the performance of polymer coated NMOFs.</p><!><p>Magnetic resonance imaging (MRI) is a noninvasive imaging technique based on the detection of nuclear spin reorientations in a magnetic field. MRI provides excellent spatial resolution, high soft tissue contrast, and large penetration depth. However, MRI is intrinsically insensitive and generally used for the detection of water protons which are present in high molar concentrations in biological specimens.50 Large doses of contrast enhancement agents, typically small-molecule Gd chelates, are used in approximately 35% of all clinical scans to enhance the contrast between normal and diseased tissues.51 Gd chelates provide T1-weighted, or positive, signal enhancement. Superparamagnetic materials such iron oxide nanoparticles are clinically used for T2-weighted or negative signal enhancement.52 The effectiveness of a MRI contrast agent is expressed by the relaxivity value (r1 for positive enhancement and r2 for negative enhancement), with agents possessing large relaxivities providing more effective contrast.</p><p>The effectiveness of Gd3+-containing NMOFs as T1-weighted contrast agents was first demonstrated by Lin and co-workers who showed that 3 and 4 possessed r1 values about an order of magnitude higher than that of Omniscan, a clinically used small molecule contrast agent, at 3T (Figure 5, Table 2).28 A number of other studies have been published since, supporting the finding that Gd3+-containing NMOFs can exhibit extraordinarily high MR relaxivities.28,29,39,47,48,53,54 Many of the Gd3+-containing NMOFs could also act as T2-weighted contrast agents, which is not possible using small molecule Gd chelates (Figure 5 and Table 2). As previously mentioned, the size and aspect ratio of 3 could be manipulated by changing the w value of the microemulsion. The relaxivity values of the nanoparticles showed an inverse dependence on nanoparticle size, with the smaller nanoparticles possessing larger r1 relaxivity. It was believed that smaller nanoparticles have higher surface to volume ratios, which enhanced the exchange between Gd3+ bound water and bulk water, leading to higher relaxivities. This size dependent trend on relaxivity was also observed in Gd3+-containing NMOFs synthesized by Kimizuka and co-workers.39 Boyes and co-workers were able to tune the relaxivity of 3 by polymer surface modification.47,48 Hydrophilic polymers led to an increased r1 relaxivity, while hydrophobic polymers increased the r2 relaxivity compared to the unmodified nanoparticle. The differences in relaxivities were explained by increased or decreased polymer water retention.</p><p>As the toxicity of Gd3+ ions is now well established,55 the in vivo utility of Gd3+-containing NMOFs is uncertain. Lin and co-workers have developed Mn-based NMOFs for T1-weighted contrast enhancement.32 Mn2+ ions have been shown to be potent MRI contrast agents with lower toxicity than free Gd3+.56,57 Reaction of Mn2+ with BDC led to nanorods of Mn(BDC)(H2O)2 (6), which were 50–100 nm in diameter and up to several micrometers in length. Blocklike nanoparticles of Mn3(iBTC)2(H2O)6 (7, iBTC = 1,3,5-benzene-tricarboxylic acid) of 50–300 nm in diameter were obtained when iBTC was used in place of BDC. The NMOFs showed modest r1 relaxivity (Table 2), but acted as reservoirs to selectively release large doses of Mn2+ ions to achieve T1-weighted signal enhancement. 7 was coated with a thin silica shell and functionalized with a cancer targeting peptide. MRI demonstrated increased uptake of the targeted nanoparticle, which was confirmed by confocal microscopy and ICP-MS studies (Figure 6). 7 was evaluated in vivo and demonstrated T1-weighted signal enhancement in the liver, spleen, and aorta 1 h after injection. This signal enhancement was believed to result from the Mn2+ ions released from the NMOF.</p><p>Horcajada and co-workers synthesized a series of iron-carboxylate NMOFs as T2-weighted contrast agents.30 These crystalline NMOFs ranged in size from 50 to 350 nm, matching known bulk phase materials of MIL-89 (8), MIL-88A (9), MIL-100(10), MIL-101-NH2(11), MIL-88Bt (12), and MIL-53 (13). Pegylated versions of 9 (PEG-9) and 10 (PEG-10) were also synthesized. 9, PEG-9, 10, and PEG-10 showed high r2 relaxivity (Table 2) on a per metal basis. 9 was evaluated in Wistar rats (Figure 7). Negative enhancement of the liver and spleen was observed after injection of 9, which dissipated 3 months postinjection, indicating the accumulation, degradation, and clearance of 9. Iron oxide nanoparticles have also been encapsulated within other NMOFs as guest species.35,58</p><!><p>Optical imaging is widely used in biological studies. Typically visible light is used to excite dye molecules within a tissue, which fluoresce at longer wavelengths. This technique is ubiquitous for in vitro and ex vivo studies but is limited by poor tissue penetration in in vivo applications.59 A number of NMOFs have been synthesized which are inherently luminescent, but have not been evaluated as biomedical imaging agents.28,29,39,60–63 The luminescence of these NMOFs is not ideal for biomedical imaging applications due to its nonoptimum absorption properties and low quantum yields. Lin and co-workers were able to create NMOFs containing a phosphorescent Ru(bpy)32+ derivative as the bridging ligand and Zn2+ (14) or Zr4+ (15) metal connecting points (Figure 8).64
15 was coated with a layer of amorphous silica, functionalized with PEG, and targeted to cancer cells. Confocal microscopy studies using human lung cancer cells demonstrated increased uptake of the targeted nanoparticles (Figure 8), which was confirmed by ICP-MS analysis.</p><p>In some cases, the optical dye was incorporated within the framework either postsynthetically or as a guest species.25,35,37,39–41,60 For example, silica coated 7 was modified with both a fluororophore and targeting peptide.32 Confocal microscopy showed increased uptake of the targeted particle by cancer cells, confirming the MR imaging results (Figure 6b–d). Lin and co-workers functionalized 2a with a Bodipy-based fluorophore (Bodipy-2a) at 5.6–11.7 wt % loadings.25 Intact Bodipy-2a was not fluorescent due to iron quenching, but it exhibited strong fluorescence upon NMOF decomposition. Confocal microscopy of silica coated Bodipy-2a showed dose dependent cellular localization and fluorescence. Boyes and co-workers modified the surface of 3 with a PNIPAM-co-PNAOS-co-PFMA copolymer (3a).48 This polymer contained fluorescein and a succinimide group for further functionalization. 3a was targeted to cancer cells and its uptake in canine FITZ-HSA cells was investigated by fluorescence microscopy. The targeted nanoparticle showed cellular localization after 1 h of incubation and cellular internalization after 24 h, while untargeted 3a did not show any localization or uptake. Kimizuka and co-workers created a series of NMOFs based on lanthanide ions and nucleotides.37–39,60,65 Anionic dyes, such as perylene-3,4,9,10-tertacarboxylate, were incorporated within NMOFs of adenosine 5′-monophosphate and Gd3+ (perylene-16). Confocal microscopy showed the uptake of perylene-16 into the lysosomes of HeLa cells and its biodistribution was studied in a murine model. Ex vivo analysis showed that perylene-16 accumulated and remained in the liver for up to 48 h post-injection, with no fluorescence observed in the kidneys, lungs, or spleen. Lanthanide-nucleotide NMOFs were used to successfully encapsulate other anionic dyes and negatively charged quantum dots as well.37–39</p><!><p>CT imaging is based on specimen attenuation of X-rays and can provide 3D images with excellent spatial resolution.66,67 High Z number elements such as iodine, barium, and bismuth are typically used as CT contrast agents; however, they must be administered in large doses (tens of grams) to achieve adequate contrast. A nanoparticle platform can thus provide superior contrast enhancement. Lin and co-workers constructed NMOFs containing I4–BDC and either Cu2+(17) or Zn2+ (18).33 CT phantom studies showed that both nanoparticles possessed slightly higher X-ray attenuation factors than iodixanol, a commercially used contrast agent (Figure 9). The higher nanoparticle attenuation results from the contributions of the metal centers. NMOFs should provide an interesting platform for incorporating other high Z elements for CT imaging.</p><!><p>Current small molecule drugs are often limited by their nonspecific distribution throughout the body, leading to high doses, rapid clearance, poor pharmacokinetics, and high side effects. Many of these drawbacks can be alleviated through the use of nanoparticulate formulations. Nanoparticles often possess superior pharmacokinetic profiles, so incorporating a drug within a nanoparticle can lead to improved efficacy. The clinical success of nanoparticle therapeutics such as Doxil and Abraxane illustrate the power of this approach, and many other nanoparticle-based therapeutics have shown promise in clinical trials.18 Lin and co-workers have developed two NMOF platforms to deliver cisplatin-based chemotherapeutics.24,25 NMOF-1 was built from a cisplatin prodrug DSCP and Tb3+ ions using a nanoprecipitation procedure. 1 was coated with a thin layer of silica (1a) and targeted with a silyl-derived peptide (1b) to cancer cells. When 1a is placed in physiological medium, the framework decomposes and the cisplatin prodrug diffuses through the silica shell in a controlled manner (Figure 10a). 1b possessed similar cytotoxicity against human colon cancer cells as cisplatin, while 1 and 1a were less effective, presumably due to increased uptake of 1b via receptor mediated endocytosis. Iron(III)-carboxylate NMOF 2a was also postsynthetically modified to contain a cisplatin prodrug, c,c,t-Pt(NH3)2Cl2(succinate)(OEt) (cisplatin-2a, Figure 10b).25 Silica-coated cisplatin-2a with a RGD peptide targeting ligand demonstrated comparable cytotoxicity to cisplatin in vitro. 3a could also be modified to contain methotrexate, which showed similar cytotoxicity against FITZ-HSA cells to the free methotrexate.48</p><p>Horcajada and co-workers encapsulated a number of therapeutics within the iron-carboxylate NMOFs 8–11 and 13.30 These synthesized NMOFs were soaked in drug solutions for loading. The anticancer drug busulfan could be loaded into 9 at 5 times the loading of previously reported systems. In vitro cytotoxicity assays showed that busulfan-loaded 9 possessed the same activity as the free drug against several cell lines. 9 was also loaded with triphosphorylated azidothymidine, an anti-HIV drug. In vitro assays showed that loaded 9 possessed significant anti-HIV activity. Maspoch and co-workers encapsulated several anticancer drugs as guest species within NMOFs synthesized from Zn2+ and 1,4-bis(imidazol-1-ylmethyl)benzene (19).36 These drugs were encapsulated within 19 with modest efficiency (≈20 wt %) and showed fast drug release. In vitro assays performed with doxorubicin-loaded 19 showed comparable cytotoxicity to that of free doxorubicin. Iron carboxylate NMOFs such as 2a, 3a, and 8–13 possess considerable potential to act as theranostic agents, as these NMOFs were utilized as both imaging contrast and drug delivery agents;25,30 further work is needed to demonstrate the real-time monitoring of drug uptake and treatment efficacy.</p><!><p>The development of NMOFs as biomedical imaging and drug delivery agents is in its infancy when compared to other nanocarriers. Nonetheless, NMOFs have already shown great promise as a new nanocarrier platform owing to the structural and chemical diversity, mild synthetic conditions, and the ability to carry a diverse array of imaging and therapeutic agents in unprecedentedly high loadings. We foresee that many other imaging agents and drugs will be incorporated into NMOFs in the future by taking advantage of the totally tunable nature of NMOFs. Particularly, combining both imaging and therapeutic agents in the same NMOF platform should greatly facilitate the efficacy studies of this promising class of theranostic nanoparticles. NMOFs also need to be further refined by using biocompatible components and by achieving more effective surface functionalization to ensure prolonged blood circulation, evasion of the RES system, and better tissue specificity. Although there have been considerable amounts of in vitro efficacy studies on NMOFs, no systematic investigation of in vivo efficacy has been launched yet. Such systematic in vivo studies are needed in order to optimize the performance of NMOFs. Optimized NMOFs should have a bright future in biomedical imaging and drug delivery.</p>