the Tumor Microenvironment with Nanoparticles



Fig. 1
Schematic illustration of the major cellular and noncellular components of the tumor microenvironment (TME). The EPR effect facilitates nanoparticle (NP) accumulation. However, high interstitial fluidic pressure (IFP), pericyte coverage, and the basement membrane limit NP extravasation from the blood vessels toward the interstitial space. When NP extravasate from the blood vessels, stroma cells and the extracellular matrix act as another barrier to further inhibit NP diffusion



Most nanotechnology research focuses on improving NP penetration and diffusion to tumor cells, and not on distribution of NP to other cellular components in stroma. Endothelial cells, TAFs, or tumor, associated macrophages (TAM), have been recognized as major components that promote cancer progression, therapy resistance, and metastasis formation [4447]. The modulation of these stromal cellular components by either small molecules or nanodrugs can facilitate the remodeling of tumor blood vessels or ECM. In addition, imaging of the TME by NP that target stroma cells increasingly contribute to accurate diagnosis, early response evaluation and treatment guidance. In this review, we discuss the barriers to NP delivery, and provide strategies to overcome these limitations. We also summarize NP that are designed to target stroma cells in vivo, discuss their diagnostic application in tumor imaging and the paradoxical therapeutic effects induced by stroma cell damage and depletion [4850].

Finally, we propose possible strategies to overcome the heterogeneity of solid tumor patterns, the complexity of stroma cells in NP delivery, and also mention the NP-based diagnostic and therapeutic applications in metastatic tumors.



2 Paradoxical Features of the Tumor Microenvironment Impacting Nanoparticle Accumulation and Penetration



2.1 Abundant Neovasculature and EPR Effect Promote Nanoparticle Accumulation in Tumor


Nano-based formulations have shown promising antitumor effects compared to free drugs due to improved pharmacokinetic properties and preferential accumulation in the tumor with abnormal vasculature [5153]. Intravenously injected nanodrugs are delivered into the pathological lesions through arterioles and released from capillaries. Therefore, the key mediators of nanomedicine intratumoral delivery are small vessels, especially capillaries [7]. Normal capillaries are lined by a tightly sealed endothelium, firmly attached and supported on the abluminal side by stellate-shaped pericytes, which are further enveloped in a thin layer of basement membrane (BM) [54]. In normal tissues, pericyte coverage of the endothelial abluminal surface varies among different organs and blood vasculatures, with a general range between 10 and 70 % [54, 55]. The vasculature BM, with major components of type IV collagen, laminin, entactin (nidogen), fibronectin, usually envelops blood vessels with a thickness ranging from 100–150 nm [56, 57]. Unlike normal blood vessels, tumor vasculatures usually have large pore openings (0.1–3 µm in diameter), leading to significantly higher vascular permeability and hydraulic conductivity [58, 59]. In addition, the extent of pericyte coverage on tumor vessels is typically diminished compared to normal tissues [54]. Both pericytes and BM are loosely associated with the endothelial cells and partially penetrate deep in the tumor parenchyma [6, 36, 54, 60]. This inherent leaky and loosely compacted vasculature tends to be abnormally permeable to macromolecules and NP (10–100 nm, in diameter). When coupled with impaired lymphatic drainage, the EPR effect brings several advantages in theranostic NP-based drug delivery (Fig. 1).


2.2 Functional Nanomaterials for Therapeutic and Diagnostic Applications in Cancer


Nanomedicine-based therapies refer to active pharmaceutic ingredients encapsulated into or conjugated with nano-based delivery vehicles, including liposomes, polymer micelles, polymer-drug conjugates, dendrimers, and macromolecule (Fig. 2) [6]. The particle size of these nanovectors ranges from 10 to 100 nm, which prevents first-pass elimination in kidneys, in turn allowing accumulation in tumors via the leaky vasculature. Biocompatible polymers such as poly-ethyleneglycol (PEG) and targeting ligands such as antibodies, peptides, and small molecules have been attached onto the surface of liposomes to achieve increased circulation time and cell internalization [61, 62]. Examples include the doxorubicin-liposome Doxil and the vincristine-liposome Onco TCSs [63, 64]. Doxil increases the half-life in the blood due to the chemical coating of PEG. It is effective in the treatment of hypervasculatured tumors, including Kaposi Sarcoma and Ovarian Cancers [63]. PEGylation has also been used to prepare polymer-drug conjugates. Another attractive polymer employed to formulate drug conjugates is N-(2-hydroxyproyl) methacrylamide (HPMA). A number of HPMA products are currently in clinical trials due to their desirable attributes, such as hydrophilicity, functionalizable side chain and biodegradability. Examples include a HPMA copolymer paclitaxel formulation in phase I trial for treating solid tumors [63]. Abraxane (~130 nm albumin-bound paclitaxel NP) is another paclitaxel formulation, which is one of the only two FDA approved nano-formulations in clinical trials besides Doxil. Though various NP formulations have been developed to target tumor cells inducing cell apoptosis, only modest survival benefits have been achieved. One possible reason is that the abnormal tumor vasculature and the dense interstitial matrix hinder delivery of the drug throughout the entire tumor in sufficient concentration.

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Fig. 2
Multi-functional nanoparticles (NP) for diagnostic and therapeutic effects in the treatment of tumors. Examples include: liposomes, polymer-drug conjugates, polymeric nanoparticles, micelles, antibody-drug conjugates, dendrimers, metal NP and quantum dots

Another clinical application of NP is cancer imaging. Precise imaging of tumor cells and their microenvironment provides accurate diagnosis and treatment guidance [65]. In the past decades, several theranostic NPs have been designed to target tumor. These include magnetic and iron oxide NP for magnetic resonance imaging (MRI), surface modified iodine, gold, and bismuth NP for X-ray computed tomography (CT) and fluorescent labeled dextran NP, silica NP, and surfaces stabilized quantum dots for fluorescence imaging [65]. Preferential internalization of certain imaging NP by stroma cells provides the possibility of imaging the TME [65]. Visualization of the TME not only contributes to disease diagnosis, but also underlines the integral distribution pattern of NP, which can subsequently guide therapeutic NP treatment.

Although, more and more imaging agents and nanodrugs are emerging based on the EPR effect, there are still many obstacles to overcome for an effective tumor diagnosis and therapy. Limited intratumoral penetration, disparate stromal cell distribution and response are two major barriers for imaging and therapy.


2.3 Barriers for Extravasation of Nanoparticle from Blood Vessel into Extracellular Matrix



2.3.1 High Interstitial Fluid Pressure (IFP) Limits NP Convection


On one hand, high permeability of the tumor vessels and a lack of functional lymphatic vessels results in the EPR effect, driving NP extravasation; on the other hand, these phenomena lead to high IFP, limiting NP extravasation. In normal tissues, IFP is around 0 mm Hg; whereas tumors, exhibiting interstitial hypertension, have an IFP almost identical to the microvascular pressure (with a range of 10–40 mm Hg) [6668]. High IFP limits convection of NP, paradoxically promoting passive diffusion [69]. Diffusion is a much slower transvascular process than convection, especially for the transport of large NP [14]. Moreover, stroma cells compress intratumoral blood and lymphatic vessels, which consequently impairs blood flow, leading to blood stasis, loss of function, and further inhibition of NP penetration [70]. The vascular abnormalities can also cause hypoxia and acidosis. Hypoxia renders tumor cells resistant to both cytotoxic drugs and radiation, while also inducing genetic instability and selecting for more malignant tumor cells with potentially metastatic properties [59, 71]. Finally, because of the steep drop in IFP on the edge of tumors, intratumoral fluid can escape from the tumor periphery into the surrounding tissue, expulsing therapeutic NP, and also excreting growth factors (e.g., VEGF-A, PDGF-C) to facilitate tumor progression [14]. Altogether, the high IFP and abnormal vasculature pose a formidable barrier to both the delivery and efficacy of nanodrugs.


2.3.2 Pericytes Coverage as One Factor to Explain Limited Nanoparticle Extravasation


Pericytes are a ubiquitous part of the TME [54, 72]. They were first identified in 1923 and named based on their function as a major constituent of mural cells lining against microvessels [73]. Although no specific molecular marker has been identified specifically to pericytes, alpha smooth muscle actin (α-SMA), PDGFR-β, NG2 proteoglycan, RGS5, and XlacZ4 are commonly used [54, 73, 74]. Signaling pathways implicated in the development of pericytes and their interactions with endothelial cells have recently been reviewed in detail [54]. Briefly, pericytes recruitment involves multiple pathways in a tumor type-specific manner. They are recruited mainly by endothelial cells through PDGF-BB/PDGFR-β signaling. Alternative recruitment signaling includes HB-EGF, pericyte-expressed EGFR and SDF-1α/CXCR4 [7577]. VEGF-A, a potent mediator of endothelial sprouting and neovascularization, acts as a negative regulator of pericyte function and vessel maturation [78]. Therefore, VEGF-A and PDGF-BB coordinately regulate pericyte coverage. Ablation of pericytes by anti-PDGF antibody or VEGF has been reported to increase vascular tortuosity and tumor growth in low PDGF-BB tumor models [79, 80]. This is paradoxical, since one would expect that increased leakiness of blood vessel with low-pericyte coverage would severely facilitate NP extravasation and inhibition tumor cell proliferation.

The relationship between pericyte coverage and NP extravasation has been investigated in detail by various groups [1, 8183]. Different from the initial assumption that all tumor microvessels have low and loose pericyte coverage [54], emerging evidence has demonstrated heterogeneous pericyte coverage within in one single tumor or with regards to different tumor types. By defining pericytes as α-SMA positive cells attached to endothelial cells, Kano et al. has classified malignant tumors into high pericyte coverage and low-pericyte coverage subtypes [81, 82]. They further established that more coverage relates to a worse prognosis and more fibrotic interstitium for pancreatic, diffuse-type gastric cancer, clear cell renal cell carcinomas, and glioblastoma (60–70 % coverage), when compared to low-coverage cancers with a better prognosis such as colon cancer and ovarian cancer (10–20 % coverage) [73]. Disparate intratumoral NP transport in response to cytokine-mediated modification of pericyte coverage has been observed in these two types of tumors in a series of work by Kano et al. [73, 8183]. Murine colon cancer CT26 is an example of low-pericyte coverage tumor, while the BxPC3 pancreatic model has been characterized by hypovasculature with more than 70 % pericyte (Fig. 3). They compared the effects of three types of kinase inhibitors, including TGF-β inhibitor (LY364947), PDGF-B signaling inhibitor (imatinib), and VEGF inhibitor (Sorafenib) on extravasation of a modeled NP, 2 MDa dextran, and a liposomal formulation, Doxil, on CT26 and BxPC3. By using the BxPC3 model, they are able to show that the TGF-β inhibitor can improve 2 MDa dextran and Doxil penetration, leading to enhanced tumor inhibition (Fig. 3). This is due to the fact that low-dose TGF-β inhibitor can block pericyte proliferation without affecting the function of endothelial cells and tumor cells. Consistent with this finding, various types of TGFβ inhibitors, including small kinase inhibitor and its nanoformulation (Fig. 4), siRNA and antibodies have been shown to decrease pericyte coverage. These inhibitors increase vessel leakiness and improve the intratumoral penetration of sub-100 nm NP, including PEI-PEG-coated MSNP, liposome, and polymeric micelle in other high pericyte coverage tumors, such as diffuse-type gastric cancer and 4T1 breast cancer models [8286]. This finding enabled delivery optimization of various contrasting media. Two recent studies have indicated that TGF-β knockdown can improve MRI contrast [87, 88]. In contrast to the finding in the BxPC3 model, TGF-β inhibitors cannot increase particle penetration and improve therapeutic outcome in CT26, since the pericyte coverage was too low to achieve any additional effect. Interestingly, the VEGF inhibitor, Sorafenib, increased extravasation of 2 MDa dextran in the CT26 model (Fig. 3). Inhibition of VEGF-A can efficiently diminish nonfunctional microvessels with low-pericyte coverage while increase pericyte coverage in the functional microvessels. Thus, the tumor vasculature is “normalized.” The increased pericyte coverage and tumor vasculature normalization were also observed by McDonald’s group [89]. Recent research by Jain’s group indicated that normalization of tumor blood vessels not only improves small molecule-based chemotherapy, but also facilitates the delivery of nanomedicine with smaller sizes [90]. Therefore, tumor vessel normalization is one explanation for enhanced NP penetration after treatment with a VEGF inhibitor in a CT26 tumor model. The combination of a VEGF inhibitor with Doxil can synergistically inhibit CT26 tumor growth. Thus, the relationship between pericyte coverage and NP extravasation varies with regard to the original pericyte coverage, blood vessel stabilization, and extracellular content. Pericyte coverage is an indispensable factor for vessel stabilization and maturation. Neither leaky, unmatured blood vessels with little coverage, nor over-matured vessels with abundant pericyte coverage are suitable for NP delivery. Moreover, pericyte coverage is just one of many factors that influence the intratumoral transport of NP. We need to take the other barriers into consideration when proposing strategies for the improvement of NP delivery.

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Fig. 3
Effects of VEGF inhibitor (Sorafenib) and TGF-β inhibitor (LY364947) in the CT26 or BxPC3 model. a Vascular phenotypes revealed by immunofluorescence staining. Green, CD31 or platelet endothelial cell adhesion molecule (PECAM)-1; red, NG2. b Extravasation of 2 MDa dextran from vasculature. Dextran is shown in green and CD31/PECAM-1 in red. Scale bars = 100 μm. c and d are schemes that explain the different effects of VEGF inhibitor and TGF-β inhibitor on high or low-pericyte coverage tumors (Reproduced from Kano 2009, copyright of Elsevier)


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Fig. 4
Two wave nanotherapy was used to treat BxPC3 xenografts with high pericyte coverage. The first wave was MSNP loaded TGFβ inhibitor (TGFβi-MSNPs and the second was MSNP loaded gemcitabine. a Double staining of endothelial cells (CD31, green) and pericytes (NG2, red) in two treatment groups. The first wave TGFβi-MSNPs can significantly decrease the coverage of pericytes (red, NG2) on the endothelial wall (green, CD31). b Fluorescent images of tumor sections to show that TGFβi-MSNPs improve the extent of liposome intratumoral distribution in the BxPC3 xenografts. In b, liposomes were labeled with Texas-red, blood vessels were stained for CD31 (green) and pericyte was stained for NG2 (blue) (Reproduced from Meng et al. 2013, copyright of ACS publishing group)


2.3.3 Basement Membrane as Another Biophysical Barrier for Nanoparticle Extravasation into Interstitial Space


The BM is a specialized form of ECM that functions as a scaffold for endothelial and mural cells. The main components of the BM are laminin and type IV collagen, which form distinct sheet-like dispositions linked together by nidogen and heparin sulfates [56, 60]. In normal tissues, more than 99 % of blood vessels are covered with a thin layer of BM. It supports the architecture of the blood vessels and regulates vessel development through gradual secretion of pro-angiogenesis and proinflammatory cytokines, such as TGF-β and TNFα [36]. In contrast to normal blood vessel BM, the BM of tumor microvessels is primarily continuous but conspicuously abnormal [36]. Heterogeneous BM morphologies exist in different regions of the same tumor or different tumor types. The first type of BM is characterized by a loose association with endothelial cells. Spontaneous pancreatic islet cell tumors in RIP-Tag2 mice, MCa-IV breast carcinomas, and Lewis Lung carcinomas belong to this type of tumors [57]. Murine lung cancer 3LL and pancreatic cancer BxPC3 are marked by a second type of BM, with a distribution of brighter collagen nodules condensely overlapped with the capillary. The third type of BM can be observed in the 4T1 model. This model has a larger collagen content, which is completely dissociated from blood vessels. Different from the interstitial matrix, another category of ECM, BM does not induce elevated interstitial pressure, yet functions as a sieve to modulate extravasation of free drug and NP from capillaries into the TME.

Extravasation of 1 nm doxorubicin (DOX), 50 nm macromolecule FITC-tagged dextran and 80 nm PEGylated liposomes were evaluated on the BM/vessel overlapped 3LL model and the BM/vessel dissociated model 4T1. Results indicated that the extravasation pattern of small molecules (including DOX and dextran) were comparable, suggesting that vascular collagen could only modulate the transport of small molecules to a limited extent [57]. However, the extravasation of liposomes was significantly different between these two types of tumors. Extravasation only occurred from the vessels that were not tightly covered by collagen type IV. An in vitro collagen sleeve model was further developed to mimic collagen surrounding capillaries [57, 60]. Collagen sleeve thickness, which was modeled by changing the number of collagen fiber layers and the size of collagen mesh (with 50–200 nm openings) were evaluated to study their effects on passive diffusion behavior. Since the molecular size of DOX is substantially smaller than any opening in the mesh, both thickness and mesh size failed to provide any resistance. However, diffusion of particles with size larger than 100 nm could be severely impeded by mesh size and thickness. Therefore, the collagen type IV density, mesh size, number of layers, and association with vessels by itself could potentially be a biophysical barrier for limiting drug extravasation and therapeutic efficacy.

Angiogenesis of blood vessels requires degradation of collagen IV by recruiting metalloproteases MMP2 and MMP9, providing a transient niche with a leaky tumor vasculature, loose and thin BM, that is beneficial for NP delivery [91, 92]. However, this transient disruption of contact between endothelial cells and vessel BM leads to endothelial apoptosis and the formation of collagen fragments that antagonize angiogenesis. On the other hand, the residual nondegraded collagen IV accumulates during repeated remodeling, resulting in multiple distinct layers of BM. During the formation of multiple layers, Collagen density increases while mesh size decreases, generating a more resistant pattern for later NP penetration. Furthermore, the underlying cells can regenerate along the surviving BM that acts as a template or scaffold for generating axons, which renders NP diffusion even harder [36].

In conclusion, BM remodeling is a complicated and controversial procedure controlled by angiogenesis. In addition to digesting the BM via intravenous dosing of collagen IV degradation enzyme, closely monitoring angiogenesis process and dosing NP at the optimal interval is required to improve NP extravasation.


2.4 Extracellular Matrix Components Determine the Interstitial Transport of Nanoparticles and Macromolecules


Diffusion of NP across the thick interstitial matrix is the last step to approaching tumor cells. For tumors with a less interstitial matrix, such as melanoma and colorectal cancers, NP can easily diffuse across the interstitial barrier, access tumor cells and induce growth inhibition. However, for tumors with a thick interstitial matrix, this process is more intractable. In contrast to BM, whose major component is collagen IV in the form of sheet-like structure, the tumor interstitial matrix consists of a highly interconnected network of collagen fiber structures (mainly collagen I, II III) that interact with other molecules, such as proteoglycans and glycol aminoglycans [9395].

Collagen content is the major determinant of interstitial transport [14]. Tumors rich in collagen inhibit diffusion to a greater extent than tumors with low collagen content. Recent studies showed that matrix modifiers such as bacterial collagenase, relaxin, and losartan (Fig. 6), an antifibrotic collagen I inhibitor, could modify the collagen network in tumors and improve the intratumoral spread of polystyrene NP, oncolytic virus HSV particles and Doxil [9698]. Apart from collagen content, the orientation of the fiber net can also influence particle diffusion. During the development of tumors, collagen remodeling enzymes modify the architecture of the collagen scaffold from early, thin and relaxed collagens (curly fibrils) to thick, linearized, and aligned fibrils (Fig. 5a). Linearization of the collagen matrix stiffens the ECM, which thereafter not only elicits diverse effects on cellular differentiation and migration, but also narrows the interfiber spacing, reducing particle motility [41]. Alignment is one determinant of collagen crosslink and NP distribution. Stylianopoulos et al. established a mathematical model to evaluate particle diffusion across collagen fibers varying in degrees of alignments. This study indicates that the orientation of fibrils leads to diffusion anisotropy (Fig. 5b, c) [99]. An in vivo NP distribution study performed by Diop-Frimpong et al. further confirmed this concept [96]. In the MU89 tumor with a more aligned and organized collagen fiber network, penetration and diffusion of NP were more restricted to a limited direction and area, while in the HSTS26T tumor model, with a dense but more diffusive, less fiber-like collagen network, particle penetration was more scattered and diffusive (Fig. 5c, d).

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Fig. 5
The influence of collagen crosslinking and alignment on NP distribution. a The architecture of the collagen scaffold changes from early thin relaxed structures (curly fibrils) to thick, linearized, and highly aligned structures during malignancy development. (Reproduced from Egeblad et al. 2010, copyright of Elsevier) b Typical fiber structure established in vitro using a mathematical model. c Diffusion anisotropy as a function of the particle radius over the fiber radius for the fiber structures employed in the study. Results indicate that the more aligned one has a more strict distribution direction. (b, c reproduced from Stylianopoulos. 2010, copyright of Elsevier. Detailed description refers to the original manuscript.) d Immunostaining of collagen I in the two in vivo tumor models. Mu89 has highly aligned fibril structure that separate tumors into different compartments, while HSTS26T has dense collagen but less fibril structure. Losartan treatment can decrease the collagen content in both tumors. e A scheme hypothesis for losartan treatment in the two tumor models with a different collagen pattern. It indicates that the aligned and highly cross-linked tumors have limited NP perfusion after Losartan treatment, while the less fibril-like tumors have more scattered NP perfusion after Losartan treatment (d, e reproduced from Diop-Frimpong et al. 2011, copyright of National Academy of Sciences of the United States of America)

The difference in the collagen crosslinking pattern causes disparate NP diffusion and leads to different therapeutic outcomes. Since collagen crosslinking is predominantly catalyzed by enzymes such as lysyl oxidase (LOX), regulated by fibronectin and organized by SPARC (secreted protein acidic and rich in cysteine), these molecules can be used as interesting target candidates to inhibit collagen crosslinking and fibril network organization [41]. For example, Kanapathipillai et al. designed a nanocarrier-based delivery system, a PLGA-conjugated LOX inhibitory antibody, to actively target to ECM. It decreased collagen crosslinking, inhibited tumor growth and metastasis, and improved therapy [6, 100].

Another determinant of interstitial transport is the glycosaminoglycan content. Hyaluronan (HA) is a nonsulfated glycosaminoglycan in the interstitial matrix. It consists of glucuronic acid disaccharide/N-acetyl glucosamine repeats of variable length and signals through CD44 to regulate receptor tyrosine kinase and small GTPase activity [101]. HA is implicated in the process of epithelial to mesenchymal transition, angiogenesis, and chemo resistance [102]. Anionic repeats of HA also capture mobile cations and solvate water, resulting in osmotic swelling and high interstitial pressure [103]. In pancreatic ductal adenocarcinoma (PDA) and the KPC pancreatic model, a clinically relevant genetically engineered mouse model (GEMMs) established by Tuveson et al., HA staining covered almost 100 % of the tumor sections and is predominantly associated with the desmoplastic stroma [101, 104]. HA depletion is reported to reverse the quiescent state of endothelium, induce fenestrae, and impair junctional integrity through disrupting CD44-dependent reorganization of endothelial actin cytoskeleton [101]. The ultrastructural changes and the vascular re-expansion lead to IFP reduction and have a multiplicative effect on intratumoral diffusion and convection [101]. Consistent with this finding, systemic administration of a PEGylated human recombinant PH20 hyaluronidase (PEGPH20), increases macromolecule permeability and augments chemotherapy responses in the KPC pancreatic model [98]. Intratumoral administration of bovine hyaluronidases also shows promise in several xenograft models [105, 106]. No recent study has shown effect of HA degradation on particle penetration, yet the specificity of this effect to the tumor suggests utility as a promising combinatory component to improve the delivery of agents with larger particle size [107] (Fig. 6).

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Fig. 6
Immunostaining of collagen I (red) (a) and quantitative analysis of collagen I content (b) in different treatment groups indicate that Losartan treatment can significantly decrease collagen content in both MU89 and HSTS26T tumors. NP penetration was further investigated. Fluorescence labeled NP was intravenously injected and tumors were then harvested to evaluate the NP penetration, c is the frozen slice to visualize NP distribution intratumorally, and d is the quantitative analysis of NP distribution. Results indicate that Losartan treatment can increase NP penetration, e and f are the growth inhibition curves of different treatments. Losartan can promote an antitumor effect in both MU89 and HSTS26T tumors (Reproduced from Diop-Frimpong et al. 2011, copyright of National Academy of Sciences of the United States of America)

Other than nonsulfated glycosaminoglycan, sulfated glycosaminoglycan can also affect interstitial transport. On one hand, these elongated and thin fibers increase the viscosity of the interstitial fluid; on the other hand, they also carry a highly negative charge, which can inhibit the transport of macromolecules or NP by forming aggregates [14]. For example, the electrostatic interaction between heparan sulfate and the diffusing NP decreases the diffusion coefficient of the NP by three orders of magnitude [108].


2.5 Strategies to Improve Therapy


From the aforementioned evidence, we conclude that insufficient transport of diagnostic and therapeutic NP in tumors results from the abnormal structure and function of tumor vessels and the dense ECM in the desmoplastic stroma. Therefore, therapeutic strategies to enhance drug delivery have focused on either remodeling the tumor vasculature to increase the function of the vascular network and decrease the interstitial pressure, or remodeling the tumor interstitial matrix so that NP can extravasate the capillary walls and penetrate faster and deeper inside the tumor.


2.5.1 Remodeling of Tumor Vasculature


The EPR effect improves NP accumulation in tumor microvessels, whereas the tortuous vessel structure, compressed diameter, deficient function, high interstitial pressure, abnormal pericytes, and BM coverage limit NP extravasation from blood vessels into the interstitial space. Therefore, tumor blood vessels are considered as potential targets to improve the therapeutic potential of nano-formulations. One strategy is to remodel tumor blood vessels to a leakier state by decreasing pericyte coverage, BM thickness, or by reducing interstitial pressure to facilitate convection. TGF-β receptor antagonists (including small molecule kinase inhibitors and siRNA) were the most frequently used therapeutic agents to inhibit pericyte recruitment and BM activation [109]. The combination of TGF-β antagonists with NP has shown enhanced particle diffusion and promising therapeutic outcome. TGF-β inhibitors were also found to lower interstitial hypertension. Decrease in IFP instantly increases vessel permeation. In addition to TGF-β inhibitors, VEGF inhibitors such as bevacizumab or anti-VEGF antibody can significantly decrease IFP. A monoclonal antibody against VEGF reduced glioblastoma IFP by more than 70 % [58, 110]. Similar results have been demonstrated elsewhere in other types of cancer [111, 112]. Tumor IFP can also be lowered by using PDGF antagonists [58]. Tumors suitable for this type of treatment, such as pancreatic cancer (APC) and 3LL murine lung cancer, usually have hypovasculature, compressed vessels, extremely high IFP, thick pericyte coverage, and BM coating.

Another strategy is the so-called normalization of blood vessel (Fig. 7) [34, 71, 90]. This treatment type is suitable for tumors marked by hypervasculature with tortuous structure and less pericyte and ECM coverage. VEGF inhibitors decrease IFP and facilitate particle perfusion. Moreover, VEGF blockage (for e.g., using of VEGF receptor-2 blocking antibody DC101) prunes immature vessels, facilitates the recruitment of pericytes, decreases vessel density and diameter, and remodels the vasculature to more closely resemble the structure of normal vessels (Fig. 7a) [34, 90]. Agents with indirect anti-angiogenic effects, such as trastuzumab, can also lead to vascular normalization. A recent study indicated that transient vessel normalization can improve the performance of small anticancer molecule reagents [71]. Vessel normalization might compromise the transvascular transport of large NP (>100 nm) due to the decrease in pore size, but recent research indicates that it can improve the permeability of small hard NP (12 nm quantum dots) and soft NP (50 nm dextran) (Fig. 7b) [82, 90]. Strategies for blood vessel remodeling have to be adapted, based on tumor structure and particle size. In addition, radiotherapy and hyperthermia conditioning can also lead to transient leakiness of blood vessel and thus improve the intratumoral delivery of NP [113, 114].

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Fig. 7
Vessel normalization improves NP delivery. a Proposed role of vessel normalization in the response of tumors to anti-angiogenic therapy. a Normal vessel structure. b Tumor vasculature structure. Tumor vessel is structurally and functionally abnormal, providing resistance to the delivery of small molecules and NP. c Dynamic vascular normalization induced by VEGFR blockade. (Reproduced from Carmeliet et al. 2011, copyright of Nature publishing group) b Effects of vascular normalization on NP delivery and therapy in 4T1 and E0771 tumors. a NP penetration versus particle size in orthotopic 4T1 mammary tumors in response to normalizing therapy with DC101. NP concentrations (denoted by pseudocolor) are relative to initial intravascular levels, with vessels shown in black. b Penetration rates (transvascular flux) for NP in E0771 tumors in mice treated with DC 101, a and b indicates that normalization improves 12 nm NP penetration while not affecting 125 nm penetration. Scale bar, 100 μm. c Cytotoxic nanomedicine effectiveness by vascular normalization. Quantification of tumor growth rates based on the time to reach double the initial volume. Abraxane (10 nm) and Doxil (100 nm) monotherapy induce growth delays versus the control treatment. Normalization with DC101 enhances the effectiveness of the 10 nm Abraxane, but does not affect that of the 100 nm Doxil (Detailed description refers to the original manuscript, Chauhan et al. 2012, copyright of Nature publishing group)


2.5.2 Remodeling of Tumor Microenvironment


The ECM, particularly the collagen and glycosaminoglycan content, limits NP diffusion. To improve drug penetration, a common strategy is to degrade these components and increase the accessibility of the diffusing particles. In addition to hyaluronidase and collagenase mentioned in previous sections, matrix MMP-1 and MMP-8 are proteases frequently used to decrease the level of tumor glycoaminoglycans and improve convection [14, 115].


2.5.3 Design of Nanoparticle to Improve the Delivery


Besides remodeling of the TME, particle size also plays an important role to enable high-level NP penetration into tumor elements. The smaller the particles the better the transport. Notably, free drugs with smaller sizes can diffuse more rapidly than NP. However, small molecules not only distribute to normal tissue inducing adverse effects, but also fail to be trapped in the tumor tissue for optimized efficacy. Therefore, the size of NP needs to be optimized for each tumor and its metastasis sites Using dextran of various molecular weights in a FaDu tumor model, variable distribution relative to molecular weight has been demonstrated [73, 116]. In this study, 3.3 kDa dextran resembling small molecule drugs entered all tumor tissues quickly. 70 kDa dextran gradually extravasated the blood vessels into the ECM, while 2 MDa dextran remained in the vascular lumen. Polymeric micelles are one kind of NP used widely to delivery hydrophobic chemotherapy drugs. In another study, Cabral and Kataoka et al. prepared a series of micellar nanomedicines (micelle DACHPt) with a diameter ranging from 30 to 100 nm. They found that penetration of NP decreased significantly upon increasing the particle size. Only small particles (30 nm) could penetrate the poorly permeable pancreatic cancer model, BxPC3, and caused promising therapeutic effect (Fig. 8) [85]. In addition, Pain’s work using PEGylated quantum dots further inferred that diffusion of NP with smaller sizes (10–20 nm) can be increased after vasculature normalization, similar to free drugs. However, particles around 100 nm cannot achieve a similar effect [90]. These observations emphasize the importance of tailoring the diameter of NP products, even those with a diameter less than 100 nm.

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Fig. 8
a Structure of a DACHPt micelle. b Mapping of platinum atoms from DACHPt of varying sizes in BxPC3 xenografts by μ-SR-XRF 24 h after administration of micelles. Scale bars, 50 μm. This microdistribution figure indicates that small particles have better intratumoral distribution. c Antitumor activity of DACHpt micelles with different diameters. Smaller micelles have better antitumor activity. Detailed information refers to the original paper (Reproduced from Cabral et al. 2011, copyright of Nature publishing group)

In addition to particle size, the shape and surface charge of therapeutic NP also plays a key role in extravasation and interstitial transport. For example, cationic particles are more likely to target endothelial cells and exhibit a higher vascular permeability compared to its anionic and neutral counterpart [117]. While extravasated into the interstitial space, cationic particles can aggregate with negatively charged hyaluronan, and anionic particles can aggregate with positively charged collagen. Therefore, neutral particles diffuse faster and distributed more homogeneously inside the tumor interstitial place [118]. As for the influence of particle shape, it is reported that linear, semi-flexible macromolecules can diffuse more rapidly in the ECM than spherical particles with similar size [119]

Though condensed ECM functions as a barrier for NP diffusion, it can also be taken advantage of to improve the efficacy of nanomedicine. Based on the acidic pH, reduced oxygen pressure, and enzyme-rich properties of the TME, NP can be constructed to the advantage of these properties. For example, a multistage quantum dots embedded gelatin NP was engineered to degrade gradually and release 10 nm small quantum dots in response to MMPs, zinc-dependent endopeptidases that are abundant in the ECM [120]. Drug-polymer conjugates have also been designed with a cleavable linker, which is the substrate of MMP and fibroblast activation protein (FAP), a gelatinase that is expressed on TAFs [121124]. Upon penetration of the ECM, free drug is released upon linker cleavage and diffuses more rapidly than the NP in the interstitial space for better therapeutic outcome. Based on this concept, pH sensitive particles have been designed to trigger the release of free drug from the cargo within tumor elements [125, 126]. In addition, external stimulants, such as electric pulses, magnetic field, ultrasound, heat, and light can also be used to improve NP penetration and free drug release [127131].


3 The Relationship Between Nanoparticle Subtumoral Distribution and Tumor/Stroma Biological Interaction


In the previous section, we described the stroma as a physical barrier for NP extravasation from blood and diffusion into tumor cells. We then proposed methods to promote NP accumulation and improve diagnostic and therapeutic effects. Apart from being a physical barrier, the stroma, especially stroma cells, also support tumor growth through a direct cell adhesion interaction or in a paracrine manner mediated by secreted factors. Therefore, stroma cells and noncell components can be recognized as potential targets for antitumor therapy. In a preliminary experiment with a human bladder cancer model, we have quantified the intratumoral distribution of DiI-labeled liposomes and observed that around 20 % of liposomes were passively internalized by TAFs, one of the major stroma cells (Data not published). This raises the following questions: What is the amount of NP accumulated in the interstitial space that are actually internalized by tumor cells? What kind of stroma cells have taken up the accumulated NP? What is the response of stroma cells to the therapeutic NP? Will the stroma-tumor interactions be affected by NP assaulted stroma cells? These questions await answer in future experiments.


3.1 Nanoparticles that Target Endothelial Cells


NP resident within the tumor vasculature first encounter layers of endothelial cells and are ready to be internalized by them. Nontargeted PEGylated NP was internalized by endothelial cells through a low-density lipoprotein receptor-mediated pathway or other alternative pathways in vivo [132]. Since therapeutic strategies for regulating endothelial cells can result in tumor shrinkage via decreasing oxygen and nutrients supply, some nanomedicines are designed to actively target endothelial cells and increase cellular internalization. Targeting endothelial cells evades the stroma barriers and decreases the potential of drug-mediated resistance based on the genetic stability of endothelial cells. In addition, some endothelial cell markers also exist on the tumors, making these NP a dual targeting agent with a broad-spectrum of effects [65]. Integrin ανβ3 is preferentially expressed on angiogenic endothelium in malignant tissue and widely used as an endothelial target [65]. Many recent studies have shown that functional therapeutic NP (loaded with doxorubicin, or antiangiogenesis agent) modified by integrin targeting peptide or cyclic or linear derivatives of RGD oligopeptide ligands can result in a strong inhibition of tumor growth [133135]. RGD modification can also be used to improve vasculature imaging. For example, iRGD conjugated super-paramagnetic iron oxide NP (SPIONs) are able to image integrin ανβ3/β5-positive tumor neovasculature in vivo through MRI [136].


3.2 Nanoparticles that Target Macrophages


Preclinical studies indicate that TAMs represent an attractive target since they have been identified as an independent poor prognostic factor in several tumors types [47]. Antibodies, such as anti-CSF-1R, have been used to target TAMs and showed promise [47]. Since TAMs have a high expression of mannose receptor, mannose has been used as a targeting ligand for NP-based TAMs delivery [137, 138]. Many NP have also been engineered to image TAMs for diagnostic purposes [139]. The recognition that MRI-compatible nanomaterials can label TAMs dates back to the mid-1990s and has recently found renewed interest. Macrophage-specific PET imaging agents are also being developed [139]. TAMs were previously viewed as agents dispatched by the immune system to attack and eliminate tumors (M2 macrophage). However, extensive research over the past decade implicates that a sub-group of TAMs, known as M1 macrophages, has antitumorigenic properties [47]. Therefore, current focus has been shifted from exclusively depleting and imaging all TAMs to modulating the ratio of M1/M2 macrophages for improved therapy. Therapeutic NP should be able to target M2 macrophages, inhibiting M2 function or converting them into an antitumorigenic M1 subtype.


3.3 Nanoparticles that Target TAFs


TAFs are mesenchymal-like cells playing key roles in transformation, proliferation, and invasion of tumors [33, 140]. The majority of TAFs originate from trans-differentiation of resident fibroblasts, pericytes, or adipocytes in response to tumor secreted growth factors such as TGF-β, endothelin-1, and fibroblast growth factor 2 (FGF2). Alternatively, TAFs can also derive from distant sources such as bone marrow-derived mesenchymal stem cells (MSCs) [33]. Homing of MSCs to neoplastic sites induces their trans-differentiation into more aggressive α-SMA, fibroblast activation protein (FAP), tenascin-C and thrombospondin-1 expressing TAFs, and pericytes. In addition, TAFs can stem from epithelial cells following the initiation of an epithelial–mesenchymal transition, or from endothelial cells undergoing endothelial to mesenchymal transition (EndMT) [44, 46, 141]. TAFs synthesize and secrete ECM and regulate the release of degrading enzyme and growth factors. TAFs can activate angiogenesis through TGF-β mediated secretion of VEGF-A, or through recruiting of circulating endothelial progenitor cells [33]. TAFs can also secrete cytokines, such as CXCL12, to direct tumor lung metastasis or tumor immune invasion through binding with CXCR4 on remote premetastatic niche [142].

Recent research indicates that several passively diffused therapeutic NP can specifically distribute to TAFs and induce cell death. Cellex, a docetaxel-conjugate NP developed by Murakami et al., is a good example of this [143]. Cellex is a 120 nm NP that can reduce α-SMA content by 82 and 70 % in the 4T1 breast cancer model and the MDA-MB-231 model, respectively, native docetaxel and Abraxane exert no significant antistromal activity. Recently in our own lab, lipid-coated calcium phosphate NP encapsulating chemodrugs and siRNAs (LCP), and lipid-coated cisplatin NP (LPC) with cisplatin as both carrier and anticancer agents have been synthesized [15, 144, 145]. Both LCP and LPC NP can penetrate the TME barrier and distribute to TAFs. In a recent study, Zhang et al. indicated that a combination of gemcitabine LCP NP and cisplatin LPC NP can target TAFs and block α-SMA positive fibroblast recruitment by more than 87 % after multiple injections in a stroma-rich bladder cancer model (Fig. 9) [53]. In another study, cisplatin was also reported to deplete TAFs when co-delivered with an mTOR inhibitor in PLGA NP (Fig. 10) [146]. Transient depletion of TAFs increased tumor permeability, suppressed IFP, increased NP accumulation, and inhibited tumor metastasis [50, 95, 147, 148]. In both Zhang and Murakami’s work, naïve TAFs are very sensitive to docetaxel and cisplatin, and show significant stromal depletion post single injection (Fig. 9). The mechanism of NP passively diffused to TAFs is not discussed in detail in the two aforementioned manuscripts. One possible reason may be that the majority of TAFs, especially α-SMA positive pericytes were localized around endothelial cells. When NPs are extravasated from the capillary wall, they immediately encounter these TAFs, which lead to their preferential internalization. Suitable particle size and materials with a high TAFs affinity can also explain the TAFs distribution. A significant depletion of α-SMA positive cells at the initial dose may also result from different responses of TAFs and tumor cells to therapeutic NP. That is to say, NP can be internalized by both tumor cells and TAFs. However, the latter has a lesser proliferating rate is more sensitive to chemotherapy and is less likely to induce resistance.

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Fig. 9
Combination of GMP LCP NP and cisplatin LPC (Combo NP) target α-SMA positive TAFs and suppress tumor growth in a stroma-rich bladder cancer model. a Tumor growth inhibition of different formulations on stroma-rich tumor bearing mice. Combo NP showed the most significant antitumor effect. a TEM of GMP LCP NP. b TEM of cisplatin LPC NP. b The distribution of TAFs (α-SMA, green) and blood vessels (CD31, red) in the stroma-rich model. c Effect of Combo NP on the induction of apoptosis and inhibition of TAFs. Then, tumor bearing mice were further treated with a single injection of combo NP and tissues were collected and analyzed every day post injection. (From d to h). d Double staining for SMA positive TAFs (red), TUNEL (green) and apoptotic fibroblast (yellow). e Quantitative results for TUNEL-positive cells and α-SMA positive fibroblasts. f Quantitative results for apoptotic fibroblasts expressed as the percentage of total apoptotic cells and fibroblasts. f Masson’s trichrome stain for collagen (blue). g Quantitative results for collagen expressed by the area (%). α-SMA positive TAFs. Collagen decreased significantly on the fourth day post single injection (Reproduced from Zhang et al. 2014, copyright of Elsevier)

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Jan 31, 2017 | Posted by in ONCOLOGY | Comments Off on the Tumor Microenvironment with Nanoparticles
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