The Role of Particle Geometry and Mechanics in the Biological Domain

Authors

  • James P. Best,

    1. Department of Chemical and Biomolecular Engineering, The University of Melbourne, Parkville, Victoria 3010, Australia
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  • Yan Yan,

    1. Department of Chemical and Biomolecular Engineering, The University of Melbourne, Parkville, Victoria 3010, Australia
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  • Frank Caruso

    Corresponding author
    1. Department of Chemical and Biomolecular Engineering, The University of Melbourne, Parkville, Victoria 3010, Australia
    • Department of Chemical and Biomolecular Engineering, The University of Melbourne, Parkville, Victoria 3010, Australia.

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Abstract

Nanostructured particulate materials are expected to revolutionize diagnostics and the delivery of therapeutics for healthcare. To date, chemistry-derived solutions have been the major focus in the design of materials to control interactions with biological systems. Only recently has control over a new set of physical parameters, including size, shape, and rigidity, been explored to optimize the biological response and the in vivo performance of nanoengineered delivery vectors. This Review highlights the methods used to manipulate the physical properties of particles and the relevance of these physical properties to cellular and circulatory interactions. Finally, the importance of future work to synergistically tailor both physical and chemical properties of particulate materials is discussed, with the aim of improving control over particle interactions in the biological domain.

1. Introduction

In the past few decades a diverse spectrum of particulate delivery systems have been developed, with sizes ranging from a few nanometers to micrometers. Among these delivery systems, drug-loaded liposomes and albumin nanoparticles have reached clinical application and have shown increased efficacy and minimized toxic side effects in the treatment of cancer.1 These successes promise momentous advances in healthcare, as these particulate systems offer a number of advantages over traditional therapy2 including: i) improved single or multiple therapeutic loading while shielding potentially fragile or toxic components; ii) tailored pharmacokinetics to evade mononuclear phagocytic system (MPS) clearance,3, 4 allowing for optimized biodistribution;5 iii) subcellular targeting to deliver therapeutics to the intracellular site of action; iv) overcoming subcellular barriers, such as drug pump-related multidrug resistance (MDR);6 and v) triggered therapeutic release in response to specific physiological stimuli.7

The preparation of particulate carriers typically involves “bottom-up” approaches, due to the inherent high degree of molecular-level specificity afforded. Polymersomes and liposomes,8–12 polymer capsules,7, 13, 14 mesoporous particles,15 along with polymer,16–18 gold,19, 20 carbon,21, 22 and silica21, 23 nanoparticles have been fabricated using this approach. Only recently have several “top-down” methods, such as PRINT (particle replication in nonwetting template) or microlithography, been explored to fabricate delivery systems for biomedical applications, largely owing to the ability to precisely control shape, size, and scalable production.24–26 Efforts have been directed to the control of chemical properties such as surface functionality and cargo release. Surface functionalization is achieved using a variety of conjugation chemistries, including thiol/disulfide, biotin/avidin and alkyne/azide coupling, and affords increased control over particle interactions in biological systems. Hydrophilic polymer brushes, such as poly(ethylene glycol) (PEG), may be used to improve circulation times due to reduced bio-fouling and opsonization,27, 28 while surface-conjugated targeting moieties such as ligands or antibodies can selectively promote the interaction with specific tissues or cells.29, 30 Coupling chemistries have also been employed to engineer triggered release in particulate systems;13, 31–33 reducible disulfide linkages under cellular concentrations of glutathione34, 35 and cleavage of hydrazone-doxorubicin conjugates under acidic conditions36 are notable examples. Using these approaches, a range of therapeutics, including small cytotoxic compounds, peptides and siRNA, have been successfully delivered in vitro and in vivo.1, 35, 37–39

In addition to the effect of bulk and surface chemistry, more recent studies have shown that the physical properties of particle delivery vectors also have a profound effect on the blood circulation dynamics and lifetime, biodistribution, and cellular interaction and uptake.40 To ultimately control the in vivo performance of particle systems, both theoretical and experimental biological studies of material elasticity, deformability,41–48 and geometry40, 46, 48–52 have been undertaken. This Review focuses exclusively on the fabrication and characterization of advanced particle delivery vectors with variable physical properties such as size, shape, and elasticity and implications of these properties upon biological interactions and material performance.

2. Particle Geometric Ratio

While the influence of particle size on circulation clearance, cell-uptake mechanisms, and flow effects has been studied in detail,7, 19, 53–55 only recently has it been reported that shape, roughness, and the resulting surface area of particles may also have a significant impact upon biological response.40, 56 Because these geometric features, including size, shape, and surface area, interdependently affect biodistribution and cellular uptake, an integrative parameter, namely the surface-area-to-volume ratio (SAV), may be used in analyzing these systems. It can be noted that the SAV increases when the particle size decreases and the geometry becomes more complex, as can be seen for the systems in Figure 1.

Figure 1.

Impact of particle geometry upon the surface area to volume ratio (SAV). A 5.5 μm diameter sphere (top left, SAV → 1) displays a reduced SAV when compared to biconcave RBCs (top right), while the internal volume (V1) is held constant. Additionally, as particle size decreases toward a 350 nm diameter nanosphere (bottom left), the SAV increases dramatically, and even more so for a long filomicelle (bottom right) with an equal internal volume to the nanosphere (V2).

A trend can be noted in the literature describing a logarithmic decrease in phagocyte uptake with increasing SAV due to flow alignment effects, whilst cellular uptake into target cells increases logarithmically due to improved surface interaction. Therefore, this chapter will first address progress in fabricating nonspherical particles, followed by an analysis of recent literature on how the geometric components of particulate systems affect blood flow dynamics, cellular uptake and intracellular dynamics.

2.1. Nonspherical Particle Fabrication

Fabrication of particles with controlled sizes can be achieved with relative ease through adjustment of discrete fabrication parameters on both micro- and nanoscales.57–60 Although good examples exist of nonspherical particle systems (Figure 2), obtaining a high degree of control over particle shape still remains a challenge, limiting investigation into high SAV particulate drug-delivery systems. Recently, review articles have focused on the fabrication of nonspherical drug delivery carriers,61, 62 and as such, synthetic methods will not be discussed in great detail here, but will be briefly addressed to provide context for the current review.

Figure 2.

Images of nonspherical particles. a) Transmission electron microscopy (TEM) image of cylindrical 1 μm diameter polymer particles in HeLa cells fabricated using PRINT. Reproduced with permission.24 Copyright 2008, Springer. b) Scanning electon microscopy (SEM) images of RBC shaped PLGA particles generated using electrohydrodynamic jetting. Reproduced with psermission.153 Copyright 2009, National Academy of Sciences. c) SEM of high-aspect-ratio triangular prisms fabricated using flow lithography. Reproduced with permission.26 Copyright 2006, Nature Publishing Group. d) SEM image of long PLGA particles fabricated using mechanical stretching.52 e) SEM image of discoidal particles fabricated using a combination of microlithography and reactive ion etching. Reproduced with permission.25 Copyright 2010, Elsevier. f) SEM image of PS vase fabricated using direct replica transcription from silica. Reproduced with permission.177 Copyright 2006, Nature. g–j) TEM images of surfactant-stabilized gold nanorods with increasing aspect ratio. Reproduced with permission.129 Copyright 2010, Elsevier. Scale bars are 100 nm (g–j), 1 μm (f), 5 μm (b,d), 6 μm (e), 10 μm (c).

The biological interactions of metal nanoparticles of various shapes have received much attention,63, 64 with gold nanorods being the most widely investigated due to their extensive synthesis library.65, 66 Gold nanorods have also shown potential for ablation therapy due to their strong surface plasmon resonance effects.67 Gold nanorods are generally synthesized using a surfactant-based stabilizer68 and can be simply modified with polyelectrolytes69 or PEG for low bio-fouling.20 Similarly, chemically stabilized silica-,70, 71 carbon-,72 and palladium-based73 rod structures have been fabricated with biological applications in mind. Although good growth control of nanorod systems has been demonstrated, their use is restricted by rapid renal clearance, in some cases inherent toxicities, and challenges in producing monodisperse suspensions of nanoparticles with a major axis greater than 200 nm.

In contrast to inorganic systems, the volume of recent literature describing the fabrication of nonspherical polymer particles is limited. Many techniques focus on lithographic, microfluidic, and PRINT methods, often incorporating photopolymerization,74–80 or through the self-assembly of colloids81, 82 or polymer chains to form filomicelles.83–87 In addition, mechanically modified polystyrene (PS) and poly(lactide-co-glycolide) (PLGA) particles with a broad range of possible geometries have been fabricated through the controlled stretching of a hydrogel polymer matrix containing a dispersion of the particles.49, 62, 88–92 Although anisotropic hollow polymer capsule systems have been reported,93, 94 capsules with nonspherical shapes have not received much attention. Studies include polyelectrolyte adsorption and then dissolution of either red blood cell,95–100 bacterial,97 or large glass-fiber101 micro-templates, along with the controlled deposition of polypyrrole onto hydrogen bubbles with variable detachment geometries.102 On the nanometer scale, researchers have fabricated hollow polyeletrolyte nanotubes using pressure filters,103 nickel nanorods,104 and porous templates,105 while Muller et al. produced hollow DNA nanotubes using an electrospun fiber template that is soluble in tetrahydrofuran.106

2.2. Biological Effects

Particles of variable size and shape have been increasingly investigated in the literature due to their effect on biological systems both in vitro and in vivo. In terms of flow-dynamics, reports have shown that the SAV may affect the propagation of particles in both interstitial and intravascular compartments, margination toward capillary walls, clearance through fenestrations, and alignment and turbulence in flow fields. For cellular association, the SAV and associated curvature effects influence antibody interaction area and adhesion strength,107 opsonization,108 and internalization kinetics and mechanisms.49 The SAV also affects intracellular aspects through nuclear alignment and particle degradation. This section will therefore focus on these effects within the context of recent literature.

2.2.1. Flow Dynamics and Biodistribution

According to fundamental fluid dynamic science, the movement of a particle within a flow regime is governed by both shape and size. The size of particles administered in blood vessels may dictate their velocity and diffusion,109 while particle movement in tissue is limited by size due to steric hindrance within the extracellular matrix.49 For nonspherical particles, angular movement under flow is often described using the rotational Peclet number, equation image, which takes into account Brownian and non-Brownian motions of particles. The rotary diffusivity, Dr, is closely related to the aspect ratio of the particle, and quantifies the extent of Brownian motion. For high Pe values, anisometric particles are not prone to Brownian effects and solely “tumble” end over end periodically, as described by Jeffery.110 The rate of “tumbling”, equation image, can be quantified according to Equation 1:

equation image((1))

Where equation image is the strain rate, re is the effective particle aspect ratio, and ϕ is the angle between the long particle axis and the plane orthogonal to the flow direction.111, 112 Larson states that for a Jeffery orbit, the period of rotation increases for increasing aspect ratio. Large-aspect-ratio particles decelerate in rotational velocity when the long axis is nearly parallel to the flow direction, and accelerate otherwise.112 Mueller and co-workers verified that re, which is determined experimentally and related to the actual aspect ratio, impacts dramatically upon angular velocity, and in turn determines the particle position probability density.111 This is shown in Figure 3 for prolate and oblate ellipsoidal particles. It is important to note that a nonspherical particle will therefore spend a greater amount of time aligned with a flow field, reducing the available cross-sectional area for interaction with other particles or cells. This was recently observed experimentally in vitro by Discher and colleagues for long filomicelles, which avoid interaction with phagocytic cells, using flow rates similar to those found in the spleen.48 As the filomicelle length increased from 1 to 3 μm, uptake into macrophages decreased dramatically and logarithmically due to alignment of the filomicelle within the flow field.

Figure 3.

The effect of particle geometry on capillary flow behavior. a) The aspect ratio (re) governs the magnitude of angular velocity under simple shearing flow. Reproduced with permission.111 Copyright 2010, Royal Society Publications. b) Platelets interact heavily with the endothelial wall due to their irregular shape. 1) Tethering, 2) rolling angular velocity and activation, and 3) firm adhesion with the wall are all affected by the platelet geometry.

When investigating the effect of the SAV on the shear rate and the turbulent nature of a particle suspension within a flow regime, a modified Reynolds number, equation image, can be adopted where G is the shear rate, and ν the kinematic viscosity.113 Qi and Luo investigated the effect of aspect ratio on Rep and particle rotational state in Couette flow, and observed that particle shape had a clear impact upon Rep. The authors observed several distinct regions of Rep where independent rotational states such as “tumbling”, “wagging”, flow aligning, “log-rolling”, and “kayaking” occurred.113 In terms of particle size, Decuzzi and co-workers showed that for silica microspheres initially adhered to a flow-chamber substrate, the critical shear rate increased dramatically as the particle diameter increased from 1.3 to 5 μm,25 which is consistent with the conclusions of both Goetz et al. and Lamprecht et al.54, 55 This illustrates that particle geometry has a large influence on the shear experienced in both the capillary and vasculature, affecting cellular interaction and adhesion with immune-system cells under flow conditions.

These observations can be placed further in a biological context by examining literature describing the margination properties of particles. Margination is defined as the movement and interaction of particles toward the endothelial wall in blood capillary channels. This is a critical aspect of therapeutic delivery to endothelial cells and also in being able to exploit the enhanced retention and permeability (EPR) effect for passive delivery to tumor sites, where EPR is a size dependent process with a maximum limit of approximately 500 nm.114 Decuzzi and co-workers discussed the margination propensity of particles with different geometries, where due to the core movement of red blood cells in capillaries, there exists a cell-free layer within close proximity of the endothelial wall in which particles with little propensity for longitudinal and lateral drift would remain.115 This result was also found by Goldman et al. for spherical particles, which were found to reside within this laminar phase layer unless an external lateral force was applied.116 Nonspherical particles, however, exhibit an intrinsic hydrodynamic lateral force and torque, meaning that these particles marginate highly, interacting with the endothelial wall to a greater extent than spherical particles. This has been validated by experiments performed by Gentile and co-workers using a parallel plate flow chamber to measure the margination propensity of silica particles with different sizes, densities, and shapes.117 It was reported that while higher mass particles were overcome by gravity and moved towards the walls as expected, as the aspect ratio and SAV increased, margination increased and a greater number of particles adhered to the chamber substrate. Similarly, this is found in a biological setting for the margnination of leukocytes due to platelet aggregation altering their co-geometry,118 as well as interactions between the endothelial wall and irregularly shaped platelets, as shown in Figure 3.119

The action of natural fenestrations during circulation is inherently connected to particle geometry. Small particles with a hydrodynamic radius of 5.5 nm120 and free molecules with a size limit of 5 kDa121 are often removed in the kidney through glomerular filtration, while particles with a diameter less than 100 nm pass through fenestrations in the endothelial lining,3 and rigid particles larger than 200 nm may be filtered in the spleen.5 Larger microparticles are often cleared through phagocytic interactions with Kupffer cells in the liver or trapped in capillary beds; however, smaller particles can also be removed via endocytosis by phagocytic or non-phagocytic cells.3 Kostarelos and co-workers reported that carbon nanotube bundles with a diameter of 10 to 40 nm and length of 0.3 to 1 μm showed rapid clearance, predominantly due to renal excretion via active glomerular filtration.72 However, it was shown by Bhatia and co-workers that renal excretion of gold nanorods with a similar minor axis length could be comprehensively reduced by attaching a 5 kDa PEG outer layer using thiol chemistry, thereby increasing the hydrodynamic radius.20 In addition to particle clearance through fenestrations, an increased SAV can help exploit passive tumor targeting via the EPR effect. Bhatia and co-workers also showed that passive tumor accumulation was high for the gold nanorods due to both size effects and reduced renal clearance,20 while Decuzzi et al. reasoned that particle shape impacts heavily upon the rational design of particulate systems in the exploitation of the EPR effect.115

All of these geometry-dependant flow properties culminate in affecting biodistribution outcomes in vivo. Discher and co-workers observed that the alignment of long filomicelles in flow fields affecting macrophage interaction in vitro paralleled the in vivo behavior of long filomicelles.48 Increased length resulted in higher blood circulation half-lives and passive accumulation in the lung. When compared to spherical PEGylated stealth vehicles, which are generally cleared within a day, long filomicelles exhibited circulation lifetimes of up to five days. Muro showed that elliptical disks were able to better target the lung using anti-ICAM targeting moieties compared to a range of sphere sizes, evidenced through a high immunospecificity index (ISI).122 Interestingly for the anti-ICAM functionalized PS spheres, the smaller the diameter the better the ISI and consequently the percentage of particles in the blood was also greater, which also correlates well with the impact of SAV on critical shear and flow-alignment, as previously mentioned. Devarajan et al. found that irregular shaped glycerylmonostearate polymer lipid nanostructures (LIPOMERs) avoided macrophages in circulation, achieving high concentrations in the spleen when compared to spherical LIPOMERs, which accumulated in the liver.51 This could have important consequences for splenotropic drug delivery, due to avoiding Kupffer cell clearance while still demonstrating high spleen retention. Decuzzi et al. also recently showed that discoidal particles actively avoided Kupffer cells and consequently liver accumulation, boosting accumulation in non-MPS organs.25

2.2.2. Cellular Interaction and Uptake

It is generally suggested that phagocytosis of particles is predominantly mediated by molecular recognition between cells and particles. One important example is the presence of integrin-associated protein CD47 on red blood cells, preventing phagocytosis. Lindberg and co-workers showed that CD47 interacts with a corresponding protein on macrophages, preventing internalization.123 Besides molecular recognition, the SAV of particles also plays an important role in both phagocytosis and target cell interaction. Long filomicelles align in flow fields, reducing phagocytic association.48 Decuzzi and co-workers observed that firm adhesion between particles and cells is obtained when hydrodynamic and dislodging forces are balanced by ligand–receptor interactions combined with other adhesion forces.115 These forces have been shown to depend on shape,107, 115 and have also been extensively proven to depend on size.107, 124 Decuzzi et al. and Gao et al. both noted that geometry and ligand density, in a similar vein to membrane adhesion, will determine the rate of receptor-mediated endocytosis of particles into a cell,107, 124 while Muro and co-workers showed that high SAV elliptical disks achieve high targeting specificity for endothelial cells due to improved interaction when compared to spheres.122

Cellular uptake of particles involves endocytosis, a process of internalizing materials by engulfing them with the cell membrane. Several mechanisms, including phagocytosis, macropinocytosis, clathrin-mediated endocytosis, and caveolar-mediated endocytosis can be used for particle internalization depending on the physicochemical properties of the particles and the cell physiology. Generally these endocytic pathways differ with regard to the size of the particles. Particles larger than 0.5 μm are more likely internalized by macropinocytosis or phagocytosis, as the inherent portal size for clathrin-mediated endocytosis is about 120 nm and approximately 90 nm for cavolae-mediated endocytosis. Foged et al. investigated the uptake of PS spheres with diameters ranging between 0.04 and 15 μm, some with modified surfaces, into dendritic cells.53 It was found that the cellular uptake rate increased as the diameter of the PS spheres decreased, similar to the results of Muro et al. who reported more rapid uptake, and lysosomal trafficking, of 0.1 μm diameter PS spheres when compared to 1 μm particles.122 Muro et al. postulated that this was due to increased small particle surface interaction, witnessed through double-positive flow cytometry experiments, combined with a macropinocytosis uptake mechanism, compared to a phagocytic mechanism for the larger spheres. This size effect was also observed by Rejman et al. in a study of the compartmentalization of both 200 and 500 nm PS beads, where only the 200 nm particles were able to accumulate in late endosomal and lysosomal compartments.125 Although to a large extent particle size determines the internalization mechanism from the viewpoint of the space limits in each endocytic pathway, varied findings have suggested the interplay between size, shape and chemical properties of particles on internalization mechanisms. Hoekstra and co-workers found that clathrin-mediated endocytosis dominated for PS-based microspheres with a diameter less than 200 nm incubated with eukaryotic cells, with a shift towards caveolae-mediated internalization as the microsphere size increased.125

While the cellular uptake of particles is influenced by the size, more recent studies have also demonstrated the significant impact of the shape on cell dynamics. DeSimone and co-workers investigated cationic PRINT particles with various sizes and shapes, examining both uptake kinetics and mechanisms.126 Cylinders (150 nm × 450 nm) were internalized quicker and to a greater extent than 200 nm diameter spherical particles in HeLa cells, even though the internal volume of the cylinders was greater. By using endocytic inhibitors, it was found that the cylinders utilized multiple mechanisms to a greater extent than the spheres to enter the cells, correlating with other extensive studies by DeSimone and co-workers for 1 μm cylindrical PRINT particles with both positive and negative charges, which showed both dual clathrin-mediated endocytosis and macropinocytosis uptake routes were predominantly utilized in a range of cell lines.24 This is consistent with the observation that the increased SAV of cylinders would further promote interaction between the cationic surface and the cell membrane proteins. Mitragotri and co-workers compared the cellular internalization of 1 μm PS spherical and elliptical particles with the same internal volume in endothelial cells.52 It was found that the spheres internalized much more rapidly, however this difference was seen to decrease over time. This work was extended by examining the effect of the alignment of the particle major axis to the cellular membrane, quantified by the initial contact angle (Ω), on cell membrane penetration velocity and internalization using rat alveolar macrophages.127 Particles with their major axis oriented tangentially to the cell membrane, that is as Ω approaches 90°, exhibited dramatically reduced internalization. This was mainly attributed to the necessary expansion required to form an actin cup for phagocytosis, while similar internalization trends were seen for the static incubation of long worm-like polymer particles with phagocytes, as seen in Figure 4.15, 48 Similar time-dependant high-aspect-ratio particle alignment was also seen by Mitragotri and co-workers for elliptical disk-shaped PLGA particles tangentially aligning in the cytoplasm with the nucleus of pooled human umbilical vein endothelial cells.52 Over long time scales spherical particles were found to have a shorter average distance to the cell nucleus, which has important implications for the delivery of therapeutics that have limited diffusion coefficients in the cell cytoplasm.

Figure 4.

Phagocytosis of nonspherical particles. Images of PS disks orientated end-on (a), disks side-on (b), spheres (c), and IgG adsorbed worms (d) fabricated via mechanical stretching of spherical beads. a–c) Reproduced with permission.127 Copyright 2006, Natioanl Academy of Sciences. d) Reproduced with permission.15 Copyright 2009, Springer.

Yang and Ma also simulated the effect of Ω for different SAV nanoparticles on the penetration of a model lipid bilayer.128 They showed that the minimum driving force of the ellipsoidal particle for breaching the lipid bilayer was dependent upon internal volume, aspect ratio, and approach angle. It was also shown that the process was time dependent; with time, the ellipsoid aligned itself tangentially with the bilayer, altering the angle Ω. Placing this in context with experimental gold nanoparticle interactions with cell-lines, Chan and co-workers showed that 14 nm × 40 nm and 14 nm × 74 nm gold nanorods internalized into HeLa cells at a much slower rate than spherical nanoparticles with a diameter of 74 nm.19 This correlates well with the modeling of Yang and Ma128 and experimental work on surfactant-stabilized gold nanorod internalization into human breast adenocarcinoma cells, where increasing the aspect ratio slowed uptake.129 Chan and co-workers also demonstrated that gold nanoparticles with a diameter of 50 nm were optimal for HeLa internalization, an effect most likely due to harnessing multi-mechanism internalization, and differences in adsorption of serum proteins due to curvature effects.19 In addition to the work on gold nanorods, several groups have also studied DNA or protein delivery using carbon nanorods, and have found them to deliver effectively into the cellular cytoplasm via an endocytotic mechanism.130, 131

In therapeutic delivery applications, cargo must be often released in a controlled manner, and delivered into the cytoplasm in order to interact with the cell nucleus. In some cases, degradation and cargo release may depend upon the particle SAV. Dunne and co-workers investigated PLGA microsphere mass loss due to hydrolysis, and found that larger spheres degraded at almost twice the rate of smaller ones, primarily due to longer diffusion path lengths allowing autocatalytic degradation.132 However for a similar system, Labhasetwar and co-workers found that a 100-fold decrease in particle diameter had limited effect on bovine serum albumin release.133

3. Stiffness and Deformability

The assembly or arrangement of a material within a structure is of design importance, and the Young's Modulus (EY) is often used to characterize the intrinsic mechanical properties of the constituent materials. The stiffness or rigidity of particle systems can be affected by material variations, such as the porosity of solid particles, as well as the diameter and shell thickness of hollow systems. There are a number of approaches to tune the mechanical properties: for instance, co-assemblies affect the mechanics of colloidal structures; cholesterol incorporating liposomes51 and polymer systems doped with metal nanoparticles134, 135 exhibit increased rigidity. More frequently, the extent of chemical bonding or crosslinking in polymer systems has been used to control rigidity and EY. In separate work, the Giasson and DeSimone groups showed for hydrogel nanoparticles and microparticles, respectively, that through adjustment of the crosslinker concentration, control over EY and system stiffness could be afforded.41, 46 Fery and co-workers also demonstrated that by controlling hydrogen bonding interactions in microcapsules, the stiffness could be controlled using pH, where the stiffness was seen to reversibly increase and decrease by two orders of magnitude by cycling the pH between 2 and 6.136 This precise control over the mechanical properties of particulate systems has lead to an improvement in the characterization methods available, along with an early understanding as to how particle stiffness and deformability affect cellular interaction. These will be discussed further in sections 3.1 and 3.3.

3.1. Mechanical Characterization of Particulate Materials

Characterization of elastic properties can be achieved using two different approaches, either through bulk analysis of particulate suspensions, or through single particle investigation. For single particle techniques, while detailed information can be obtained for individual system components, collecting enough data for a meaningful statistical analysis renders it a time consuming process. However, bulk analysis data can be difficult to effectively process into information on singular elastic components due to intrinsic system effects.

3.1.1. Bulk Techniques

The use of rheological methods and systems for measuring the bulk properties of polymeric materials is quite common for macroscopic hydrogel materials,46 however, several groups have also shown that elastic information can be obtained for polymer nanoparticle systems.137 Mäder and co-workers demonstrated for lipid based colloidal drug carriers that the elastic storage and loss modulus, along with the complex viscosity of the suspension, could be elucidated using both continuous shear rheometry and oscillatory testing.138 For hollow polymer capsules, bulk elastic measurements are generally performed using either an osmotic swelling or buckling approach (Figure 5).42, 44 In this method, the osmotic pressure is controlled through the addition of polyelectrolyte either inside or outside the capsule volume, forming a polyelectrolyte-associated counterion cloud.139 This pressure exerts a force, with direction and magnitude dependent on the concentration gradient. Using microscopy techniques and noting the critical osmotic pressure at which a capsule collapses for a given shell thickness and radius, or alternatively the degree of radial swelling, both the elastic and Young's moduli can be evaluated. Möhwald and co-workers observed that this technique is limited in the accessible force range obtained, and that in situ force changes are not possible,139 while Vinogradova noted that for osmotic deformation equations to apply, the capsules must not stretch, be infinitely permeable to water, and be impermeable to small ions, further limiting the technique.44 Due to these restrictions and oversimplifications, single particle measurements for hollow polymer systems are often utilized.

Figure 5.

Mechanical characterization methods for nanoparticles and hollow capsules. a) Schematic diagram of a nanoparticle acoustic response to energy absorption, and associated vibrational spectra. Reproduced with permission.176 Copyright 2010, American Chemical Society. From thermal equilibrium (1), thermalization occurs upon excitation with an ultrafast electron (2), giving off acoustic vibration (3) and subsequent cooling (4). b) Confocal fluorescence microscopy images of osmotically buckled (left, scale 10 μm) and ruptured (right, scale bar 5 μm) polyelectrolyte capsules and c) RICM used in tandem with a colloidal-probe AFM set-up to characterize buckling events for polyelectrolyte microcapsules, where region (A) relates to a small deformation regime, (B) relates to an adhesion area increase, and (C) is capsule buckling. Reproduced with permission.42 Copyright 2004, IOP Publishing.

Due to their small size and high rigidity, metal nanoparticles are inherently difficult to analyze using single-particle techniques. Although metal nanorods and wires can be elastically evaluated using nanobeam mechanics,140 recent research has suggested that using a time-resolved spectroscopic method may allow for measurement of the mechanical properties for a wide range of metal nanoparticle suspensions.141 Using this method, the EY and linear elastic response can be determined through sample irradiation with femtosecond laser pulses and consequent measurement of the acoustic response (Figure 5).141, 142 While differences are sometimes found to exist between nanoparticle and bulk elastic properties due to size and defects in the crystal lattice, it is generally found that the elastic properties measured are similar to bulk metal properties.141

3.1.2. Single-Particle Techniques

In contrast to bulk measurements, single-particle measurements allow for a high level of control over the application of forces to each system component. One such way of achieving this is through the use of an atomic force microscope (AFM) on a single, substrate immobilized particle. Several groups have thoroughly investigated the mechanical properties of films using AFM,143–145 and recently advances in optics and force control systems have allowed for single analysis of particles. In a similar fashion to parallel-plate compression experiments, a spherical probe with a high radius of curvature is attached to the end of an AFM cantilever to effectively apply a controlled compression to a micro- or nanoparticle.146, 147 This technique has been applied to both hollow capsules43 and polyelectrolyte microtubes,101 where it has been proven that system stiffness and the EY can be derived, along with important information on buckling forces, characterized using a combination of AFM and reflection interference contrast microscopy (RICM) (Figure 5).148 Polymer particles and pressurized microgel template capsules have also been investigated using this technique,149, 150 while Erath et al. were able to measure the mechanical properties of polydimethylsiloxane microspheres adhered to a tipless cantilever.45 Similar to cell-poking experiments using a stylus,151 it has been demonstrated that the EY for hydrogel nanoparticles can be obtained using AFM with a sharp, noncolloidal, probe.41 However for a small probe, the geometry is often difficult to accurately quantify, and it may also impart an excessive axial strain leading to measurement errors in EY.

With regards to single-particle investigation using a flow-field, Doyle and co-workers observed the deformability of lithographically fabricated PEG hydrogel particles with similar sizes to red blood cells, using a 4 μm microfluidic channel.152 Similarly, the Mitragotri and co-workers, and DeSimone and colleagues independently performed capillary flow experiments to investigate the deformation extent of red blood cell (RBC) shaped particles of variable EY within a flow regime (Figure 6).46, 153 While Doyle and co-workers measured the pressure differential for particles of different shapes passing through the capillary, Mitragotri and co-workers observed the stretching of individual protein shells due to flow field effects using an optical method. Suction pressure due to micropipette aspiration was used by Hochmuth to measure the elastic properties of cells,154 while Barthès-Biesel and co-workers were recently able to quantify the elastic properties of large crosslinked ovalbumin microcapsules as a function of pH, using a cylindrical microchannel coupled with a high-speed optical set-up to model the deformation.155

Figure 6.

Studying particle deformation using microfluidics. a) A syringe pump drives the flow through the device. b) Particles with low EY are highly deformed as they pass through the fenestration, c) while particles with a high EY are not able to deform and therefore cannot pass through (scale bar 30 μm). Reproduced with permission.46 Copyright 2011, National Academy of Sciences.

3.2. Comparison to Biological Systems

Recent approaches for the design of particulate materials for heathcare applications involve tuning the elastic properties to match that of biological particles, such as RBCs.46, 153 RBCs have a circulatory lifetime of up to 120 days, are able to evade phagocytosis, and demonstrate high elastic deformation in order to pass through splenic fenestrations. However, old RBCs are removed from circulation in the spleen when the mechanical properties of the cells change, becoming more rigid.156, 157 This has inspired work aimed at designing novel particulate systems to mimic healthy RBCs, in order to increase the circulation lifetime in the body. The elastic modulus of RBCs has been measured by various groups, with Lekka and co-workers, and Mitragotri and colleagues obtaining values of 26 ± 7 kPa and 15.2 ± 3.5 kPa, respectively, using AFM techniques.153, 158 The elastic shear modulus for the RBC membrane has been determined to be approximately 10 μN m−1, determined experimentally using both shear flow159 and micropipette aspiration160 techniques. The shear modulus, important to the nature of RBCs, is quite low in comparison to most particle types, as they need to be able to squeeze through thin fenestrations, and demonstrate high reversible deformation under flow. For other cell types, cancer cell lines have been found to be elastically softer than healthy cells based upon scanning force microscopy measurements by Lekka et al.,161 and later through experiments by Gimzewski and co-workers for metastatic cancer cells from lung, chest, and abdominal cavities, compared to the benign cells which usually line these cavities.162 Lekka et al. found that the EY for normal Hu609 ureter cells was 12.9 ± 4. kPa compared to 1.0 ± 0.5 kPa for T24 bladder carcinoma cells, while it was later postulated that this decrease in elasticity allows cancer cells to metastasize or spread.163 Mooney and co-workers noted that more elastic cells were able to take up polyplexes to a greater extent, also enhancing cell proliferation and survival.164 Levental et al. also presented a summary on the elastic moduli of different biological tissues, and the testing method used.165

In comparison, synthetic systems demonstrate a wide variation in elastic modulus based upon AFM force spectroscopy characterization methods. Soft hydrogel particles vary between roughly 1 kPa to 1 MPa depending on the polymer type and extent of crosslinking within the system,41, 46 solid polymer particles such as PLGA generally have an EY in excess of 1 GPa,153 while synthetic surface-bound liposomes are much softer with an EY of approximately 3 kPa.150 It is important to note that it has already been experimentally demonstrated that the EY controls the rigidity and deformability of solid particles.46 Metal nanoparticles examined using time-resolved vibrational spectroscopy generally have an EY in the range of 10 GPa to 1 TPa, where a value of 64 ± 8 GPa has been measured for gold nanorods. This value can be compared to the bulk gold value of 78 GPa.141 For polyelectrolyte capsules, single particle AFM experiments reveal that the EY generally falls within the range of 10–1000 MPa, which represents a transition between rigid cross-linked rubber and soft glass.44

3.3. Biological Effects

Similar to the effects of the SAV on biological activity both in vitro and in vivo, particle rigidity and deformability have also been found to be important factors. Control over flow dynamics, biodistribution, and cellular interactions are also dependent upon the elasticity of particle systems, although the volume of literature is more limited than in the SAV case. However, results indicate that softer particles in general will circulate longer in vivo, and will be internalized into cells at a reduced kinetic rate, or for very soft particles even completely evade phagocytosis.166

3.3.1. Flow Dynamics and Biodistribution

Rigidity has been found to affect clearance from the bloodstream, most notably through splenic clearance. It has been postulated that the increased splenic clearance of cholesterol-modified liposomes is due to increased stiffness compared to unmodified liposomes,51 while nanoparticles not functionalized with a polymer brush layer are generally cleared very quickly via renal excretion.20, 72 Discher and co-workers found that long filomicelles display extended circulation lifetimes in vivo.48 To test the effect of filomicelle rigidity on the lifetime, the micelles were crosslinked to form solid cylinders, which were found to clear within hours compared to days for flexible systems. This led to the conclusion that the circulation time is dependent on the ability of a particle to relax and fragment in a flow stream, also affecting flow-alignment and system extension within phagocyte streamlines (Figure 7).48 Also in regards to flexibility and deformability, in order to pass through spleen fenestrations of the order of 200–500 nm wide,108 DeSimone and Petros observed that particles must either be smaller than approximately 200 nm, or be sufficiently elastically deformable to pass through and remain in circulation.33 In other work, it was shown that tuning the deformability via variation in EY allowed for large particles to pass through narrow microchannels.46 Mitragotri and co-workers observed optically the deformability of particles with a similar EY and geometry to RBCs, and found that the particles were stretched by approximately 70%, and retained their discoidal shape upon exiting the microchannel, demonstrating elastic deformation.153

Figure 7.

Flow and deformation of filomicelles in vivo and in vitro. In vivo filomicelle circulation time increases with particle length (a), while long filomicelles have been shown to deform and align in flow fields and avoid phagocytic interaction (b). Scale bar 5 μm. Reproduced with permission.48 Copyright 2007, Nature Publishing Group.

The only comparable study at this time, to our knowledge, which involves investigating the effect of elastic modulus on both circulation and biodistribution was performed by DeSimone and co-workers.46 The EY was tuned using variable crosslinking concentrations for 6 μm diameter discoidal hydrogel particles. Similar to the results reported above, with increasing EY the circulation lifetime decreased drastically, correlating well with the theory that stiffer particles are cleared from circulation more rapidly. Interestingly, in regards to a 2 h biodistribution study in mice, particles with a modulus of 39.6 ± 10.4 and 63.9 ± 15.7 kPa were predominately found in capillary beds in the lungs, while particles with a lower modulus of 7.8 ± 1.0 and 16.9 ± 1.7 kPa were able to avoid clearance in the lung and were found to accumulate in the spleen. This work highlights the importance of particle rigidity in maximizing circulatory lifetimes, and also in biodistribution control.

3.3.2. Cellular Interaction and Uptake

Compared to literature on the effect of geometry and size on cellular interaction, studies on the effect of elasticity and rigidity in this area are rather limited. While not a cell study, Fery and colleagues investigated the adhesion of hollow polyelectrolyte shells onto both flat and polyelectrolyte-covered glass substrates.167 It was found that as the shell thickness decreased, the radius adhesion area increased dramatically due to the shell becoming more flexible and deformable. This has broader implications in regards to the ligand/receptor-mediated adhesion interactions between particles and cells, where an increased adhesion area correlates toward increased particle/cell interaction. Based on recent fundamental studies, Gao et al. found that the elastic energy changes in a cell membrane mean that stiffer particles would be internalized favorably via cell wrapping when compared to softer particles, which tend to spread along the membrane.168 This factor probably influenced results observed by Wang and Beningo for interactions between opsonized microparticles with variable EY, and mouse bone-marrow macrophages.169 The polyacrylaminde particles were 1 to 6 μm in diameter and coated with bovine serum albumin, and it was found that, as the bis-acrylamide crosslinker concentration, and hence EY, increased, so did the preference for phagocytosis (Figure 8). As both surface chemical and geometric properties were kept constant between the two systems, the effect was solely ascribed to phagocytosis being a mechanosensitive process. Similarly, for 150 nm hydrogel particles, Giasson and co-workers investigated the effect of rigidity on macrophage internalization rates and mechanisms.41 Stiffer nanoparticles were seen to be taken up faster than softer particles, and by different mechanisms; particles with an EY of 18.0 ± 5.0 kPa were exclusively taken up by the RAW 264.7 macrophage cells using macropinocytosis, while particles with an EY of 211.4 ± 43.3 kPa were exclusively taken up via a clathrin-mediated endocytosis route. Interestingly, hydrogel nanoparticles with a modulus between these two values were able to be taken up via dual effective pathways, and thus internalized at a quicker rate. In terms of intracellular trafficking, Giasson and co-workers also found that accumulation into lysosomal compartments is dependent on the nanoparticle elastic modulus.41 An increasing elastic modulus generally led to increasing colocalization with FITC-labeled dextran, a common lysosomal marker, and nanoparticles were found not to be released into the cytosol. It was also found that the kinetics of early endosomal entry was elasticity dependent, where only the stiffest nanoparticle was found to be colocalized to the early endosome marker after 15 minutes.

Figure 8.

Phagocytic internalization of both antibody-functionalized stiff and soft polyacrylamide beads. a) Stiff antibody-functionalized beads (left two bars) were six times more likely to be internalized than soft beads (right two bars). This was confirmed optically for both stiff (b) and soft beads (c), where stiff beads were more readily internalized. Reproduced with permission.169 Copyright 2002, The Company of Biologists Ltd.

It can also be noted that a macropinocytosis pathway for the internalization of polyelectrolyte capsules has been observed.35, 170, 171 This is an interesting finding, as polyelectrolyte capsules generally have a material EY at least an order of magnitude greater than the hydrogel nanoparticles studied by Giasson and colleagues, indicating that the particle structure and size will strongly mediate cellular uptake.

Regarding intracellular therapeutic release, Fernandes and co-workers investigated the forces and deformations required for polyelectrolyte capsules to release their cargo,172 whilst Delcea et al. extended the work to examine polyelectrolyte capsules with different shell thicknesses and, consequently, rigidity.173 It was found that the capsule stiffness had a pronounced effect upon the applied force at which the cargo was released, and that the forces applied (0–2 μN) were within literature estimates for an applied intracellular force range. This was coupled with ex situ electroporation experiments, where it was estimated that the African green monkey kidney cells used exert at least 0.2 μN upon intracellular incorporation of the capsules,173 confirming that particles will be affected by mechanical intracellular action to different extents depending on their resistance to deformation.

4. Perspectives

Recent developments in both “top down” and “bottom up” fabrication strategies for advanced particulate systems allow for improved control over several particle physical properties, such as size, shape, and rigidity. Increasingly, evidence has shown that the geometric and physical characteristics of particles have a pronounced effect on biological interactions, where increasing either the deformability or SAV allows particles to: align in flow fields more effectively and reduce interaction with macrophages; improve cellular surface interaction under low shear conditions; and generally reduce the rate of cell uptake. Although these studies have opened new ideas and routes to control biological responses, comprehensive knowledge gaps remain. In many instances, a precise knowledge of how particle chemistry affects these physical properties remains deficient, so that tuning of particle shape and mechanics remains difficult. Further exploration of particle biomechanics will require the development of robust synthetic methodologies to allow the tuning of physical properties in a wide variety of particle delivery systems. Moreover, a detailed understanding of the complex mechanisms governing interactions between particles and biological systems, such as internalization and sub-cellular trafficking, still remain unclear.

While this Review focuses solely upon the affect of physical parameters on biological interactions, it is clear that approaches based upon controlling both physical and chemical properties are required, extending work by Gratton et al. on cylindrical polymeric particles with variable surface charge.24 While physical properties strongly influence circulatory and cellular interactions, equally important to the success of particulate healthcare materials are chemical-based properties, such as stealth, targeting, and triggered degradation.174 This is highlighted by work on the surface patterning of colloidal materials, allowing for dual chemical and active surface area modification.175 Of particular relevance is the work of Stellacci, Irvine, and co-workers, demonstrating that the patterning of alternating subnanometre striations of anionic and hydrophobic groups on gold nanoparticles, as seen in Figure 9, modulated the intracellular fate. Patterned particles accumulated in the cell cytosol as opposed to being trapped in an endosome, likely due to the patterning and related surface roughness providing a resistance to nonspecific protein adsorption.176 Although significant challenges to the field remain, we expect that future multidisiplinary work will afford an improved understanding of the mechanisms and parameters governing the interactions between biological systems and particle delivery vehicles at the circulatory, cellular, and sub-cellular level. This work will provide the foundations toward the rational design of advanced particle therapeutics with specific and optimized in vivo behavior, resulting in the more effective treatment of diseases and enhanced patient outcomes.

Figure 9.

Surface-patterning on gold nanoparticles affects cell internalization and intracellular fate. Schematic diagrams and STM images of both disordered (a) and ordered (b) patterning of hydrophilic and hydrophobic regions on gold nanoparticles. Dendritic cells show much lower levels of cytosolic accumulation for disordered (c) than ordered (d) particles incubated at 4 °C. The scale bar in (a,b) is 5 nm. Reproduced with permission.176 Copyright 2008, Nature Publishing Group.

Acknowledgements

This work was supported by the Australian Research Council under the Federation Fellowship scheme (FF0776078) (F.C.) and by the National Health and Medical Research Council (NHMRC) Program Grant 487922 (F.C.).

Biographical Information

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James Best is a Ph.D. student in the Department of Chemical and Biomolecular Engineering at The University of Melbourne, and works under the supervision of Prof. Frank Caruso. He received his Bachelor's degree in Chemical Engineering (Hons.) and Science (Chemistry) also from The University of Melbourne in 2008. His current research interests include the mechanical analysis of nanoparticles for biomedical applications using atomic force microscopy.

Biographical Information

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Yan Yan received her Ph.D. in Biochemistry and Molecular Biology from Peking University (P. R. China) in 2008. Currently, she is a post-doctoral research fellow in the Nanostructured Interfaces & Materials group headed by Prof. Frank Caruso at The University of Melbourne. Her research focuses on the interface between materials science and biology.

Biographical Information

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Frank Caruso received his Ph.D. degree in 1994 from The University of Melbourne and then moved to the CSIRO Division of Chemicals and Polymers in Melbourne to study the interfacial alignment of receptor molecules for biosensor applications. He was an Alexander von Humboldt Research Fellow and then group leader at the Max Planck Institute of Colloids and Interfaces (Berlin, Germany) from 1997 to 2002. Since 2003 he has been a professor in the Department of Chemical and Biomolecular Engineering at The University of Melbourne. His research focuses on polymers at interfaces, nanostructured colloidal systems, nanocomposite thin films, and biomaterials.