Immunological Risk of Injectable Drug Delivery Systems
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- Cite this article as:
- Jiskoot, W., van Schie, R.M.F., Carstens, M.G. et al. Pharm Res (2009) 26: 1303. doi:10.1007/s11095-009-9855-9
Injectable drug delivery systems (DDS) such as particulate carriers and water-soluble polymers are being used and developed for a wide variety of therapeutic applications. However, a number of immunological risks with serious clinical implications are associated with administration of DDS. These immunological events can compromise the efficacy and safety of these systems by changing the pharmacokinetics, biodistribution and targeting capability of DDS, and by inducing hypersensitivity reactions. Antibodies induced by administration of DDS can be directed against the carrier material, the drug and/or targeting ligands associated with the DDS. Complement activation and opsonization of DDS, which may or may not be associated with antibody formation, may lead to accelerated clearance, hypersensitivity reactions and formation of membrane attack complexes resulting in premature release of the drug. Also platelets have been reported to play a role in DDS immunogenicity. Despite our curtailed understanding of the relationships between physicochemical characteristics and immunogenicity of DDS, several risk factors have been identified. Insight into these factors should be employed in the development of novel DDS with low immunological risk.
KEY WORDSantibody responsecomplement activationdrug deliveryhypersensitivityimmunogenicityliposomesplatelet activationpolymers
Injectable drug delivery systems (DDS) play an increasingly important role in the administration of therapeutic drugs since more of these systems are becoming commercially available for a wide variety of applications. There are many different types of DDS (e.g. polymer-based nanoparticles and microparticles, lipid-based nanocarriers, water-soluble polymer–drug conjugates, etc.) and they offer several advantages over conventional dosage forms. In particular, controlled release and targeting of active substances (small molecules, proteins or genes) to the desired site of action is being exploited to improve the delivery at the target site and avoid body sites which are sensitive to toxic drug actions (1–7). Liposomal DDS like Doxil and Ambisome have been on the market already for decades, whereas other liposomal drugs are in various stages of clinical development (8,9). Also several peptide-loaded PLGA-based microparticles are available for the treatment of prostate cancer and other diseases, while PLGA nanoparticles are being developed for the (targeted) delivery of proteins, DNA and vaccines (6). Furthermore, efficient anticancer drugs based on nanosized conjugates of linear hydroxypropyl methacrylamide (HPMA) copolymers, various molecular and supramolecular structures of the HPMA copolymers and polymer micelles, conjugated with biologically active proteins, low-molecular-weight drugs and/or targeting ligands, have been developed (10,11).
Remarkably, little attention has been paid to the potential immunogenicity, i.e. the capability of a substance or device to elicit an immune response, of injectable DDS. Whereas the immunostimulatory effects of delivery systems have been well documented and exploited in the vaccine delivery field (12–14), the unwanted immunostimulatory effects of the same or similar carriers when used as DDS have received much less attention. At first instance this may not be surprising as the major drives in this field are the drug and the disease to be treated. Therefore most investigators focus on kinetic and therapeutic improvements and drug-related toxicity of the products, rather than the immunological risks associated with the administration of the DDS. However, adverse immunological effects associated with the application of DDS may pose serious risks to patients.
Immunogenicity of DDS can have severe clinical implications, such as reduced efficacy, immune responses after repeated administration of a DDS (containing the same or a different drug), or acute reactions. There is an urgent need to increase our understanding of the physicochemical characteristics that determine immunological reactions against injectable DDS already in clinical use or development, such as liposomes, poly(lactic-co-glycolic acid) (PLGA) based systems and hydroxypropyl methacrylate copolymer (HPMA)–drug conjugates (15–17). Here we will review the literature on immunological risks associated with the use of injectable DDS. Our survey is primarily focused on specific antibody-mediated responses. Immunotoxicity of DDS, which has been extensively reviewed elsewhere (7,18–22), is also addressed. Causes and consequences of immunological responses against carriers, encapsulated drugs and targeting ligands will be described and illustrated with examples. Moreover, relationships between physicochemical characteristics of DDS immunological risks associated with their use will be discussed.
ANTIBODIES AGAINST DRUG DELIVERY SYSTEMS
Antibodies Against the Carrier Material
Data on antibody responses against DDS are available mainly for liposomes (23). Lipid A-containing liposomes administered with Freund’s incomplete adjuvant (FIA, a mineral oil) in animals has been reported to induce antibodies against phosphatidyl choline and other phospholipids (24,25) as well as cholesterol if incorporated in large amounts (71 mol%) (26–28). Although anti-lipid antibodies in principle can cross-react with endogenous lipids, these antibodies are unlikely to interact with cell surfaces because these are sterically protected by coverage with large molecules such as glycolipids and proteins (23,29,30). However, formation of antibodies against liposomes may have major implications for the pharmacokinetic profile of liposomal carriers, in particular through complement activation (7,31) and opsonization (32).
The above-mentioned studies on the immunogenicity of liposomes and liposomal lipids were conducted in the presence of adjuvants. Although this may not be representative for the administration of liposomes in a therapeutic context, recent publications show evidence of antibody (mainly IgM) responses in mice and rats against non-adjuvanted PEGylated liposomes intended for therapeutic use, resulting in rapid blood clearance (33–39). Antibody responses were shown to be maintained in T cell-deficient animals but not in B cell deficient or splenectomized animals, pointing to a T cell-independent mechanism requiring marginal zone B cells in the spleen (34,36,37). Furthermore, IgM was claimed to clear PEGylated compounds far more rapidly and complete than IgG antibodies do, since the pentameric structure of IgM promotes the formation of larger immune complexes and activates complement more efficiently than IgG does (35).
Although the literature describing anti-DDS antibodies is largely restricted to liposomal carriers, there is no fundamental reason why antibodies would not be formed against other DDS, including polymeric DDS. Polymers by definition contain repeat units, which may trigger B cell activation and hence antibody production (40,41), as discussed below. Indeed the formation of anti-PEG antibodies has been observed in patients treated with PEGylated proteins and found to be correlated with accelerated clearance and reduced activity of the drugs (42,43). Also, HPMA copolymers and other water-soluble polymers have shown to be immunogenic in mice, although antibody levels are generally low (44,45). Antibodies against HPMA–drug conjugates were reported to be predominantly, though not exclusively, directed to the drug (45). Conjugation of avidin to HPMA did not affect the moderate IgM response against the polymer when administered to mice in the presence of alum (46). Repeated administration of empty polyacryl starch microparticles in mice did not induce detectable antibody levels (47).
Encapsulated drugs may increase or reduce antibody responses against the carrier. When human serum albumin was entrapped in the above-mentioned polyacryl starch microparticles, repeated administration in mice resulted in antibodies directed not only against the protein but also against the particle matrix (47). Semple et al. showed that loading of PEGylated liposomes with antisense oligonucleotide or plasmid DNA enhanced the anti-PEG antibody responses in several mouse strains (37). Interestingly, this effect was found to be independent of the presence of immunostimulatory CpG motifs in the drug. In contrast, PEGylated liposomes containing encapsulated doxorubicin induced lower IgM levels in rats than empty PEGylated liposomes did, likely due to the toxicity of doxorubicin for immune cells (33).
Antibodies Against Drugs
It is well known that conjugation of haptens (i.e., small molecules that can act as B cell epitopes if bound to a carrier) to proteins can render them immunogenic, no matter whether or not the hapten is an endogenous compound. For instance, steroid hormones and cholesterol were shown to become immunogenic in rabbits by conjugation to human albumin (48); paracetamol (acetaminophen) conjugated to horseradish peroxidase elicited anti-paracetamol antibodies in mice (49). Whereas these examples illustrate the immunogenicity of haptens conjugated to proteins, thereby providing them with T-helper epitopes, the conjugation of haptens with non-proteinaceous carriers (which lack T-helper epitopes) can also make them immunogenic. Examples include acrylamide–dinitrophenyl (DNP) conjugates (50–52), dextran-trinitrophenyl (TNP) and polyacrylamide–TNP conjugates (53), and various HPMA–drug conjugates (45).
Not only chemical conjugation but also noncovalent association of small molecules in a particulate carrier can render them immunogenic. Incorporation of gangliosides in lipid A-containing liposomes was shown to generate anti-ganglioside antibodies in mice (54). Lipid A-containing liposomes with the cholesterol precursor squalene induced anti-squalene antibodies in mice (55), showing that even very hydrophobic compounds, which presumably are buried in the liposomal bilayer, can become immunogenic by liposomal association.
Particulate systems are widely used in vaccinology to increase the immunogenicity of intrinsically immunogenic proteins, such as bacterial and viral antigens. So, the encapsulation of foreign proteins in particulate DDS is likely to increase their immunogenicity. For instance, a significant increase in IgG1 levels following subcutaneous administration in mice of foreign proteins or protein–hapten conjugates encapsulated in PLGA particles was observed in comparison with the levels after administration of the free compounds (56). Ovalbumin covalently coupled to liposomes elicited higher antibody levels than soluble ovalbumin (57). Many other examples can be found in the vaccine literature (12–14).
Although the immunogenicity of soluble self proteins is low or absent, practically all recombinant human proteins are immunogenic in patients (58,59). As discussed later, the immunogenicity of self proteins can be enhanced by presentation in aggregated or particulate form (see below). Hence, association of recombinant human proteins with a particulate DDS may be a risk factor for immunogenicity.
Encapsulation of drugs in DDS does not always lead to increased anti-drug antibody levels, e.g. when the drug is cytotoxic or immunosuppressive. Tardi et al. showed that the antibody response in mice to ovalbumin covalently attached to the surface of liposomes was fully suppressed when doxorubicin was co-encapsulated in the liposomes (57). The immunosuppressive effect of doxorubicin has been ascribed to the toxic action of doxorubicin on macrophages or B cells (33,57).
In particular cases the incorporation of a drug into a delivery system can reduce its immunogenicity. This has been reported for recombinant human factor VIII (rFVIII). Approximately 15–30% of the patients treated with rFVIII develop inhibitory antibodies that neutralize the protein’s activity. For most of these patients rFVIII is a non-self protein because they do not produce endogenous factor VIII. Ramani et al. reported that hemophilic mice treated with subcutaneous injections of phosphatidyl serine (PS)-containing liposomal rFVIII (non-self protein) produced lower total- and inhibitory titers compared to mice having received rFVIII alone (60). This effect was ascribed to steric shielding of the immunodominant PS-binding site of rFVIII and an immunomodulatory effect of PS (61). Incorporation of rFVIII in PEGylated PS-containing liposomes resulted in a further reduction of rFVIII immunogenicity (62).
Reduced anti-drug antibody formation has also been observed for polymer–protein conjugates as compared to the free proteins (44–46). Several (self and non-self) proteins conjugated to high-molecular-weight (ca. 30 kDa) copolymer HPMA induced lower antibody titers in mice as compared to the free proteins. When the proteins were conjugated with PEG (Mw 5,000) the immune response was also reduced albeit to a lesser extent, while conjugation to low-molecular-weight (ca. 3 kDa) HPMA did not reduce the immunogenicity of the proteins (45). It was hypothesized that antigenic epitopes of proteins bound to the high-molecular-weight HPMA copolymer were shielded and thereby had become unavailable for recognition by the immune system, a mechanism that has been suggested for PEGylated proteins as well (58).
The above-mentioned examples illustrate that the immunogenicity of a drug when incorporated in or conjugated with a DDS is largely unpredictable. When a drug is associated with a DDS its immunogenicity can be induced, enhanced as well as reduced.
Antibodies Against Targeting Ligands
DDS can be actively targeted to the desired site of action by covalently coupled targeting ligands, such as antibodies and receptors (1–5,63). A few reports have shown that this can lead to antibody responses against the ligand.
Philips and Dahman observed that free mouse IgG2a was not immunogenic after repeated injection in mice, whereas immunoliposomes (containing 0.9 mol% mouse IgG2a) induced anti-IgG2a antibodies (IgG1) impairing the targeting capacity of the liposomes in vivo (64). The presence of 5 mol% PEGylated phospholipid in the liposomal bilayer enhanced rather decreased the anti-IgG2a response.
Harding et al. (65) attached chimerized mouse IgG (C225, containing human Fc) covalently to the hydrazide end-groups of the PEG chains which were grafted onto the surface of liposomes. Whereas repeated intravenous administration of soluble C225 did not induce antibodies, a single injection of the immunoliposomes triggered an immune response in rats which was reflected in C225-specific (mainly Fc-specific) IgG titers. Subsequently injected immunoliposomes or free C225 were rapidly cleared from the blood circulation. This demonstrates that coupling of the IgG to liposomes renders it immunogenic.
Antibodies Against Linkers
In principle, a chemical linker to conjugate a drug or targeting ligand to a DDS, or to PEGylate a DDS, can give rise to the creation of new immunogenic epitopes, but evidence of linker-induced immunogenicity is lacking in the public domain. Since chemical linkers are sterically ‘trapped’ between the DDS and the drug or ligand moiety, especially in case of bulky ligands like antibodies, linker-induced immunogenicity may not be a major issue in most cases.
If the linker is proteinaceous in nature, e.g. avidin-biotin spacers which are commonly used in research, the linker might not only be immunogenic itself but also provide T-helper epitopes enhancing antibody responses against the DDS or incorporated drugs.
Why Do DDS Elicit Antibodies?
The previous sections have illustrated that antibodies can be formed against drug carriers, encapsulated drugs or targeting ligands. In this section we will explain why DDS-mediated drug delivery can induce antibody formation.
Relative Risk of Immunogenicity for Several Antigen Categories
Antigen presentation form
High-density multi-epitope array presentation
High-density multi-epitope array presentation combined with adjuvant
Polymers (not protein based)
Non self proteins
As many of the DDS/drug combinations for which immunogenicity has been described are non-protein based, and thus lack T cell epitopes, antibody formation should occur via a T cell independent mechanism. One common mechanism likely responsible for the formation of DDS-induced antibodies is the creation of multiple B cell epitopes by the DDS formulation, which is an intrinsic property of most DDS. Closely spaced B cell epitopes in repetitive arrays can directly activate B cells via a mechanism known for T cell-independent type 2 (TI-2) antigens (see (40) and references therein). TI-2 antigens must be repetitive to cluster and crosslink BCRs on the surface of the B cell. This BCR clustering initiates a complex signaling pathway, such as the activation of Bruton’s tyrosine kinases, which mediate B-cell proliferation leading to activation, proliferation and formation of antibodies against the antigen (40,67,68). The immune system has evolved to rigorously react to highly dense (spacing between 5–10 nm), repetitive epitope arrays that normally are present only on the surface of viruses and some bacteria, but not on mammalian cell surfaces (67). BCRs on the surface of resting B cells have been estimated to be about 40 nm apart; BCR crosslinking by epitope arrays can be achieved rapidly, since BCRs are ‘floating’ in the cell membrane of B cells and can be recruited at a velocity of ca. 300 nm/s (40).
Classical examples of TI-2 antigens include bacterial capsular polysaccharides used as vaccines (e.g., pneumococcal and meningococcal vaccines), and haptens (i.e., small molecules that can act as B cell epitopes if bound to a carrier) conjugated to polymers. In 1976, Dintzis et al. showed that acrylamide substituted with 12 to 16 dinitrophenyl (DNP) haptens were very immunogenic, while free DNP as well as polymers containing less haptens per polymer did not elicit antibodies (50). Additional investigations confirmed that the immunogenicity of haptenated polymers is determined by a minimum hapten valency of 10–20 (51,52), but depends on the size of the polymers as well, requiring a threshold molecular mass of about 100 kDa (51). Moreover, ample evidence points to epitope spacings between 5–10 nm being a potent trigger for B cell activation (50,51,67,69–73). This principle has also been proposed as a mechanism for the immunogenicity of aggregated proteins (58,59). Brunswick et al. demonstrated that conjugation of anti-BCR (anti-IgD or anti-IgM) antibodies, or Fab fragments thereof, to dextran made them 1,000-fold more potent (as compared to the unconjugated antibodies) in B cell activation (74). This was later shown to be a representative model for the activation of B cells by TI-2 antigens conjugated to polymers (75).
Chackerian et al. (72) demonstrated that the density of self proteins on the surface of virus-like particles (VLPs) is crucial for the induction of an antibody response against these proteins. The closer the spacing, the higher was the resulting antibody response, being optimal at an epitope spacing of 5–10 nm, in line with that reported for polymer–hapten conjugates. Unlike self proteins, non-self proteins were shown to elicit antibodies also when not conjugated to VLPs (72,73). This suggests that “non-selfness” is a risk factor by itself, whereas a self antigen, like a small molecule, requires multimeric presentation to become immunogenic (Table I).
The examples of polymer–hapten conjugates have illustrated how non-immunogenic molecules can be turned into immunogenic structures. It can be anticipated that presentation of the same molecules on particulate carriers will show even stronger effects, as the immune system has evolved to recognize particulate materials as foreign (14). Indeed, insoluble polyacrylamide-trinitrophenyl (TNP) beads and dextran-TNP beads with high hapten densities activated B cells much more strongly than their soluble counterparts (polymer–TNP conjugates) did (53). Moreover, polymer–drug conjugates such as HPMA based systems seem less immunogenic than particulate drug carriers. These observations are also consistent with the conception that large, rigid systems are more immunogenic than smaller, more flexible structures (40,71). The general validity of this proposition, however, remains to be established. Another explanation for the low apparent immunogenicity of currently used conjugates is that the polymers are usually much smaller than the reported threshold size of 100 kDa required for raising an antibody response (51).
Besides the particulate character and the presence of repetitive B cell epitopes, additional risk factors can be provided by the presence of adjuvants. In particular, pathogen-associated molecular patterns (PAMPs) form an important adjuvant category (76), which includes Toll like receptor (TLR) ligands such as LPS or bacterial DNA (CpG) sequences. These adjuvants are stimulators of the innate immune system, capable of activating B cell clones specific for other antigens. Whereas TLR ligands are being utilized to enhance the potency of vaccines, they should be avoided in DDS but might be present as impurities or contaminants. Furthermore, TI-2 antibody responses can be rendered T cell dependent (TD) if T-helper epitopes are contained in the carrier, e.g. when the carrier is protein based or contains protein based drugs or ligands. In theory this would result in higher and more persistent antibody levels, because—besides direct activation of B cells—other TD mechanisms and generation of immunological memory may happen.
An important consequence of antibody formation against DDS is activation of the complement. Moreover, complement has been reported to enhance the BCR crosslinking signal (40). Complement activation, however, can also occur independently of (specific) antibodies, as discussed in the following section.
IMMUNOTOXICITY OF DDS
The complement system plays an important role in the defense against pathogens, such as viruses and bacteria. One of the major functions of the complement is to label pathogens for subsequent elimination from the host. Depending on its properties, a DDS may be ‘seen’ as a pathogen and eliminated by the complement system. Consequences of DDS-induced complement activation include opsonization of the DDS resulting in rapid clearance by macrophages, hypersensitivity reactions and formation of membrane attack complexes (7,31,77), the latter being relevant for vesicular DDS.
All three pathways involve activation of C3 by C3 convertase, which cleaves C3 that is bound to the particle (pathogen or DDS) surface in the fragments C3a and C3b. C3a plays a role in hypersensitivity reactions (see below). C3b and its fragment iC3b are the most abundant and important complement proteins. Interaction of surface bound C3 fragments with the C3 receptor on the surface of phagocytic cells leads to phagocytosis of these immune complexes (41,79,82,83). For liposomal DDS the activated complement can cause liposome destabilization by the formation of a membrane attack complex (MAC or C5b-9) (7,81). MAC formation induces leakage and release of the liposomal contents, resulting in increased toxicity or reduced activity, caused by higher drug concentrations at non-target sites or lower drug concentrations at the target sites, respectively (41,79).
The classical pathway is initiated by binding of IgM and IgG to foreign particles and subsequent binding of C1q to surface-bound IgM or IgG (41,80,84,85). IgM associated with PEGylated liposomes may work synergistically with complement components (C3b, iC3b) on the enhancement of liposome uptake by liver macrophages through receptor mediated endocytosis. Complement activation is strongly amplified through a cascade of enzymatic reactions. Antibodies, especially IgM, trigger and amplify this cascade, even in small amounts, implicating that the antibody mediated process may be the predominant mechanism (35,86).
In 1997 Alving et al. demonstrated that the activation of complement by cholesterol-containing liposomes involves the classical rather than alternative pathway (87). However, later reports indicate that liposomes can activate complement via both the classical and the alternative pathway. Liposomal complement activation is promoted by large size, polydispersity, positive or negative surface charge and high (>45%) cholesterol content (31,87). It has been shown that negatively charged liposomes activate complement primarily via the classical pathway (86,88) and positively charged liposomes do this via the alternative pathway (88,89), whereas neutral liposomes are poor activators of complement (88,90).
Complement activation via the classical pathway by anionic liposomes has been reported to occur through antibody-independent binding of positively charged C1q to the surface of the DDS through electrostatic interactions (84,91). However, a recent study showed that the structure of the negatively charged moieties on the liposomes, rather than the negative charge per se, is crucial for complement activation (92). Complement activation by PEGylated liposomes has been reported to require the presence of negatively charged compounds such as PEG-phosphatidyl ethanolamine and is possibly initiated by naturally circulating anti-PEG antibodies or in an antibody independent fashion (7,90,93).
Besides liposomes, isobutylcyanoacrylate nanoparticles have been reported to activate complement in vitro. Surface modification of these particles by coating with a high-density (‘brush’ conformation) layer of chitosan or dextran reduced complement activation, whereas a low-density (‘mushroom’ conformation) layer did not (94). In the same study dextran sulfate layers were found to be poor activators of complement, but at the same time promoted the adsorption of serum proteins. Various other charged nanoparticles have been shown to be potent compliment activators in vitro as compared to neutral ones (95–97).
The clearance of liposomes and other DDS from the blood circulation occurs after recognition by cells belonging to the mononuclear phagocyte system (MPS) (81,85,98,99). Also hepatocytes seem to play a role in the clearance of liposomes from the blood circulation (100). PEG attached to DDS was initially thought to act as an inert steric barrier for attachment of opsonins, thereby leading to decreased recognition of the DDS by cells of the MPS, resulting in prolonged circulation (34,101). However, it has been shown that after repeated injection PEGylated liposomes are cleared much faster than after the first administration, a phenomenon known as the accelerated blood clearance (ABC) effect (33,35,36,38,42,102–104). The second dose of PEGylated liposomes accumulate mainly in the liver, but also to a lesser extent in the spleen, which implies involvement of Kupffer cells and fixed macrophages of the spleen in the accelerated blood clearance of subsequent doses (105–108).
The ABC effect can be divided into two phases: the induction phase, following the first injection and resulting in formation of serum factors, and the effectuation phase, following the second or subsequent injections in which PEGylated liposomes are rapidly cleared (106,107). The effect was reported to be saturable and mediated by a serum factor. It is thought that complement activation, caused by anti-PEG IgM elicited by the first dose, initiates the ABC phenomenon (37,39,104), whereas a direct effect of the liposomes on the intrinsic phagocytic activity of Kupffer cells was excluded (103).
According to Wang et al., induction of the ABC effect is not only determined by the PEG coating but also by the size and surface charge of the first dose of liposomes (104). However, Laverman and coworkers have reported that the ABC effect is a general characteristic of liposomes and does not depend on the presence of PEG or on the liposome size, but is related to lipid dose and dosing interval (106,109). This may suggest that pre-existing anti-lipid antibodies (23) or other serum components are (also) involved in the ABC effect. Early capture of liposomes by these serum components might explain why in general the first part of the concentration—time curve, especially at low liposome doses, is steeper than the following part.
Hypersensitivity reactions triggered by intravenous administration of DDS have been observed in the clinic for liposomal drugs (e.g., Doxil, Daunoxome), emulsions (e.g. taxol formulated in Cremophor EL), and polymeric micelles (e.g. Genexol, taxol formulated in PLA-PEG micelles) (31,110,111). Although the Genexol-mediated reactions were ascribed to intrinsic properties of paclitaxel, they are more likely related to the PLA-PEG micelles used in this formulation to solubilize the drug.
These anaphylactoid reactions are a consequence of activation of the complement system via the classical and/or the alternative pathway, and are called complement activation-related pseudoallergy (CARPA) (31). As opposed to IgE-mediated allergy requiring presensitization, CARPA occurs at first exposure of the DDS and its severeness usually declines after repeated administration (31,108,112–114). It is therefore unlikely that DDS-induced antibody formation plays a role in CARPA, but the involvement of pre-existing antibodies cannot be excluded. CARPA involves anaphylatoxin (C3a and C5a) liberation which causes an increase of inflammatory cells in the blood circulation. The incidence of CARPA varies between 5–45% of patients treated with DDS, which is much higher than classical anaphylactic reactions to drugs, for example penicillin allergy occurs in less than 2% of the treated patients (31). CARPA can induce serious clinical conditions which show cardiovascular, respiratory and cutaneously related symptoms, such as bradycardia, arrhythmia, tachypnea and flushing.
Platelets are known as primary actors in hemostasis. In addition, accumulating evidence points to platelets as important players in the innate immune response (115–117). It has been reported that platelets might play a bridging role between innate and adaptive immune response (115), or act as innate inflammatory cells in an immune response (116). Platelets express a variety of receptors, such as FcγR, TLR4 and TLR2, and can secrete several immune-stimulatory products, such as cytokines and chemokines (115,117,118).
Reports about DDS-induced platelet aggregation are conflicting. It has been demonstrated that liposomes are able to induce (119–121) as well as inhibit (122,123) aggregation of platelets. The types of phospholipids in the membrane of the liposomes (124–126) and the surface charge of these vesicles (119–123) seem to play a role in the procoagulatory properties. Platelet aggregation in vitro and rat thrombosis in vivo was reported to be induced by carbon nanoparticles (127), whereas neutral and PEG-coated surfactant-based nanoparticles did not induce platelet activation in vitro (128). Liposomes with a negative surface charge have been reported to increase as well as inhibit platelet aggregation (120–123).
Little is known about the mechanisms of DDS-induced platelet activation (19). One of the signaling molecules that might play a role is the platelet-activating factor (PAF). PAF is a proinflammatory phospholipid secreted by mast cells, monocytes and macrophages. It interacts with the PAF receptor expressed on cells such as platelets, monocytes and eosinophils. This can lead to platelet aggregation and a number of inflammatory effects, such as chemotaxis and degranulation (124,126), as well as anaphylaxis (129,130).
Aggregation of platelets may also be directly enhanced by the presence of immune complexes on the DDS surface. Platelets are able to recognize these immune complexes through their Fc receptor, FcγRIIa. Aggregated platelets stimulate the production of C3a and C5a, factors of the complement system that play a role in CARPA (41).
Immunological Reactions Against Injectable DDS and their Clinical Consequences
Effect on efficacy and safety
Accelerated blood clearance (ABC)
Membrane attack complex (MAC) formation
Complement activation-related pseudoallergy (CARPA)
Risk Factors for Immunological Responses Against Injectable DDS
TLR ligands (e.g. LPS, CpG)
Ligands targeted to phagocytes/APCs (e.g. mannose)
At least 10–20 epitopes per conjugate/particle
High density (5–10 nm spacing) of epitopesa
High molecular weight (>100 kDa)
Positive or negative surface charge
Large size and high polydispersityc
High (>45%) cholesterol contentc
Positive or negative surface charge
For DDS containing drugs other than immunosuppressive agents, one should consider the risk for antibody formation in the design of the DDS. Multiple epitope arrays clustered at the surface of DDS form a particular risk factor for immunogenicity and should be avoided if possible. Ligands such as mannose that are recognized by APCs should especially be avoided, except for vaccination purposes (63,131), although data showing enhanced immune responses when used therapeutically are lacking. The particulate character of many DDS makes them prone to be recognized as foreign by immune cells and the complement system. Soluble polymer–drug conjugates seem less likely to induce antibody formation. Although PEG was initially considered to be an immunologically inert polymer, also PEGylated DDS have been shown to induce antibodies and to be involved in complement activation, accelerated clearance and hypersensitivity reactions. So, PEGylation is no guarantee for an immunologically safe DDS.
The route of administration has not been systematically studied but almost certainly has a major influence on the risk of immunological responses. Whereas subcutaneous administration may be the injection route which most easily generates antibodies, complement activation and platelet activation are of particular clinical relevance upon intravenous administration.
Also other factors such as the release kinetics, release mechanism, as well as the stability of the drug and the carrier are likely to play a yet unidentified role in the immunogenicity of DDS. For instance, dependent on the residence time of a DDS, during release and decomposition of the carrier new surface structures will be created which may be more (or less) immunogenic than the intact system. Moreover, labile protein drugs in DDS are susceptible to aggregation (132), which may generate additional risk.
Antibody formation against DDS typically occurs after one or a few administrations, as opposed to antibodies against recombinant human therapeutic proteins which usually show up after chronic treatment (58,59), despite the similar mechanisms thought to be involved. The observed difference in the kinetics of antibody formation could be due to the fact that in DDS the drugs are deliberately concentrated in colloidal carriers, which are known to have immune stimulatory activities and—almost by definition—contain epitope arrays. In contrast, therapeutic proteins normally contain only small amounts of immunogenic impurities such as aggregates and therefore have a much lower probability of eliciting an immune reaction.
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