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Vascular delivery of several classes of therapeutic agents may benefit from carriage by red blood cells (RBC), for example, drugs that require delivery into phagocytic cells and those that must act within the vascular lumen. The fact that several protocols of infusion of RBC-encapsulated drugs are been currently explored in patients illustrates a high biomedical importance for the field.
Two strategies for RBC drug delivery are discussed: encapsulation into isolated RBC ex vivo followed by infusion in compatible recipients and coupling therapeutics to surface of RBC. Studies of pharmacokinetics and effects in animal models and in human studies of diverse therapeutic enzymes, antibiotics and other drugs encapsulated in RBC are described and critically analyzed. Coupling to RBC surface of compounds regulating immune response and complement, affinity ligands, polyethylene glycol alleviating immune response to donor RBC and fibrinolytic plasminogen activators is d escribed. Also described is a novel, translation-prone approach for RBC drug delivery by injecting of therapeutics conjugated with fragments of antibodies providing safe anchoring of cargoes to circulating RBC, without need for ex vivo modification and infusion of RBC.
The readers will gain historical perspective, current status, challenges and perspectives of medical applications of RBC for drug delivery.
RBC represent naturally designed carriers for intravascular drug delivery, characterized by unique longevity in the bloodstream, biocompatibility and safe physiological mechanisms for metabolism. Novel approaches for encapsulating drugs into RBC and coupling to RBC surface provide promising avenues for safe and widely useful improvement of drug delivery in the vascular system.
The optimization of vascular delivery of drugs is an important biomedical problem. This problem is especially acute in case of delivery of potent and specific, yet labile and complex biotherapeutic agents including enzymes, which in most cases require precise localization in the target site. One means to achieve this goal is coupling drugs to carriers, such as synthetic or natural polymer structures of diverse geometries, phospholipid liposomes, albumin, antibodies or other biological molecules1. Use of drug carriers promises to enhance the specificity, effectiveness and safety of therapeutic, diagnostic or prophylactic interventions. Functions of drug carriers include: i) providing the optimal drug half-life in circulation and clearance mechanism; ii) restriction of unintended drug uptake by and effects in non-target tissues; iii) targeting to the intended therapeutic site; and, iv) providing optimal timing of the action, i.e., its timely initiation and termination.
Among other carriers, erythrocytes (red blood cells, RBC, non-nuclear biconcave discs with a diameter of ~7 µm, thickness ~2 µm and plasma membrane surface area ~160 µm2) represent a potentially attractive and, in some aspects, unique carrier for drug delivery (Table 1). One microliter of human blood contains about 5 million RBC and total number of RBC, the most abundant cellular constituent of the blood (>99%), in the human body approaches 30 trillion. Human erythrocytes normally have a life span of 100–120 days (of note, mouse RBC life-time is about a third of human’s counterpart), travel ~250 km through the cardiovascular system and function as natural carriers for oxygen. RBC life-span and size markedly exceed those of other drug delivery systems (e.g., <10 h and <100 nm for PEG-modified “stealth” liposomes). Thus, RBC are attractive carriers for intravascular delivery, e.g., for prolonging drug circulation and restricting unintended extravasation2–4.
Injected substances interact with RBC, which partition and metabolize more than 50 known drugs (e.g., captopril, sulfanilamide, testosterone, insulin, catecholamines, tacrolimus, antibiotics and other agents)5. Therefore, RBC may unintentionally serve as a natural blood compartment participating in biodistribution, pharmacokinetics, slow release, metabolism and action of diverse drugs including anti-tumor agents6 and genetic materials7. However, the intentional use of RBC as drug carriers is arguably of even higher interest. This area of research has been incepted in early seventies, when it has been proposed that effects of certain drugs might benefit from encapsulation into autologous or immunologically compatible donor RBC that can be safely injected in the host, thereby improving circulation of a protected drug and its delivery to certain targets in the body8. A prolonged life-time in the circulation, availability, considerable surface and volume (mean corpuscular volume of human and mouse RBC is ~90 and ~50 µm3, respectively), high biocompatibility and natural mechanisms for safe elimination of RBC represent attractive features of this tentative drug carrier. Erythrocytes are champions among other drug delivery systems from the standpoint of longevity of circulation, biocompatibility and restriction of unintended permeation of drugs into extravascular compartments. Hydrodynamic forces driving RBC to the blood mainstream in the circulation and endothelial glycocalyx minimize RBC interaction with vascular walls9. Normally, RBC do not undergo extravasation from the circulation into tissues except hepatic sinuses and interstitium in the spleenic follicles, i.e., open to circulation sites of RBC genesis and elimination, part of reticuloendothelial system (RES). RES macrophages in the spleen and liver rapidly and effectively take up senescent, damaged and modified RBC via phagocytosis leading to their lysosomal degradation.
RBC transfer many substances in the bloodstream. Oxygen-carrying hemoglobin is the most important cargo among other molecules naturally encapsulated in the interior volume provided by erythrocyte plasma membrane. RBC membrane is supported from within by a complex cytoskeleton comprising of hexagonal lattice of actin-spectrin network interconnected with anchoring integral plasmalemmal proteins via numerous structural and connector proteins. Dynamic regulation and remodeling of this cytoskeleton maintained via activity of small GTP-ases asserts morphological stability, plasticity and deformability of RBC necessary for millions repetitive travels through tight capillaries10. As in other cell types, RBC plasma membrane represents an asymmetrical phospholipid-cholesterol composed bilayer, i.e., phosphatidylserine is enriched in the inner leaflet, whereas the outer surface is slightly negatively charged mostly due to anionic components of the glycocalyx extended from integral and surface glycoproteins associated with RBC plasmalemma, playing role of transporting (i.e., ion exchangers and channels), structural and protective elements. Glycophorin A and Band 3 represent two major integral glycoproteins among more than 300 proteins found in RBC plasma membrane11. Some of these proteins are expressed at relatively low and variable levels throughout human population, yet exert key functions of protecting RBC from damage and elimination from the bloodstream by immune system (see below).
Due to these unique natural transporting features, RBC may provide optimal type of a carrier for drugs that are either needed to be delivered into the RBC-eliminating cells such as RES macrophages, or intended to work in the bloodstream (Figure 1). In the last three decades, significant efforts have been invested in order to prove the validity of this paradigm and establish clinically applicable strategies for RBC carriage of drugs. RBC are been tested for drug delivery in numerous animal4,12–14 and human studies14. Certain challenges and limitations of using RBC as drug carriers have been identified in these studies. Thus, use of RBC modified ex vivo (e.g., using donor or autologous blood) limits treatment options to hemotransfusion settings, technically challenging for a widespread use. Further, unintentional reduction of biocompatibility of modified RBC represents a serious potential problem. However, results of recent animal studies devised approaches to solve or circumvent these problems and boost confidence that RBC-based drug delivery systems can find medical utility relatively soon. Indeed, several RBC-drug delivery approaches are currently undergoing clinical testing and industrial development. This article will review two strategies for drug delivery by carrier RBC: loading into RBC and coupling to RBC surface.
From a grossly oversimplified practical viewpoint, RBC resembles a durable sac-voyage made of elastic material. This might help explain why exploration of RBC transporting capacities in drug delivery field started with drug encapsulation inside RBC ghosts. Since early seventies, this area of research has received a substantial attention and produced first clinically tested RBC-based drug delivery systems. More than two hundred papers, monograph and proceeding chapters have been published on diverse aspects of drug encapsulation into carrier RBC; readers are addressed to the previous inclusive reviews for more complete literature references as well as more specific description of methods for encapsulation of drugs into carrier RBC15–17. Several excellent reviews outlining the ideology, methodology and outcomes of animal and human studies have been published on this subject including a recent article in this journal by one of the leading expert, Mauro Magnani16–20. It would be impossible to cover in sufficient depth all aspects of this strategy in a reasonably concise article; hence we provide rather a cursory overview of the field with focus on the most recent results and clinical studies.
Originally, RBC carriage has been proposed to improve delivery of cargoes into target cells8,21. Methods of electrical insertion and hypotonic RBC loading followed by resealing provided encapsulation of diverse agents including antibiotics, steroids, anti-microbial agents, proteins and genetic materials into RBC with loading efficacy ranging from reasonable to fair and to excellent (10% to 30% and to 70%, respectively) of drugs retaining their functional activity22–24. In vitro studies showed that encapsulated agents can be released from RBC either slowly (e.g., via diffusion through RBC plasma membrane25 and/or its eventual degradation)13,26, or rapidly (e.g., via lysis of carrier RBC by plasma complement)27,28. Early studies also showed that RBC carriers facilitated intracellular delivery of encapsulated agents including proteins and DNA into cells in culture21.
Examples of pharmacological and imaging agents encapsulated into carrier RBC include diverse enzymes29,30, fluorescent labels30, erythropoietin for sustained stimulation of hemopoietic potential31, hemoglobin cofactor inositol hexaphosphate for enhancing RBC oxygen carrying capacity32,33, anti-thrombotic drugs heparin34 and thrombolytics35, amikacin for anti-parasitic therapy36,37, insulin38, fluoro-AMP25 and methotrexate for cancer chemotherapy35, isotopes for imaging of blood pool using gamma-scintigraphy and MRI39–42, antisense oligonucleotides for gene knock-outs43 and anti-viral interventions44, plasmid DNA for gene therapy45, and, more recently, magnetic nanoparticles46.
Organ distribution, pharmacokinetics and effects of some of these drug delivery systems have been tested in studies in lab animal species32,43 and, in a more fragmentary fashion, in human patients42,47–49. Some of these studies provided rather mixed results, perhaps, due to unintended damage inflicted to carrier RBC during drug loading that compromised its biocompatibility, or variability and heterogeneity of RBC loading (noted even within the same batch in the early studies)29,30. For example, RBC-encapsulated and free erythropoietin showed similar pharmacological properties in mice and its activity in plasma was essentially gone within less than a day after injection despite the fact that tracing of 51Cr-label showed relatively prolonged circulation of drug-loaded RBC, with half-life in blood ~6 days vs 7 days for intact RBC50. However, intravenous injection in mice of antisense oligonucleotides encapsulated into opsonized RBC enhanced hepatic delivery of the cargo43, whereas injection of RBC-encapsulated plasmid DNA resulted in a relatively prolonged transfection of the transgene in phagocytic cells in the RES and blood45. A relatively stable MRI signal has been detected in the blood samples taken from mice during a week post intraperitoneal injection of RBC-encapsulated magnetic nanoparticles46.
RES macrophages and other professional phagocytes eliminating senescent and damaged RBC represent natural target for drugs encapsulated in RBC. In fact, it is rather difficult to avoid uptake of carrier RBC by phagocytes and divert delivery to other targets of interest. Drug loading into RBC inevitably causes some extent of damage to its membrane and, in some cases, internal content (e.g., depletion of RBC systems for storage and utilization of energy51 and nitric oxide transport and metabolism52). In order to avoid these complications, major efforts have been dedicated to studies of mechanisms of RBC biocompatibility, its damage upon RBC modification and means for its preservation for drug delivery applications53–58.
Conformational changes and abnormal clustering of membrane glycoproteins including major components glycophorin A and band 3 caused by cross-linking agents and RBC membrane damage by osmotic stress during drug loading53 lead to cytoskeletal dysfunctions (loss of RBC plasticity and mechanical stability55), sensitize RBC to lysis caused by oxidants59 and provoke fixation of immunoglobulins that naturally present in plasma60. Exposure of phosphatidylserine from the inner leaflet of the RBC plasma membrane61 and other components normally absent on the RBC surface augments these processes and predisposes RBC to adhesion to endothelium62. Unintentional inactivation of specific RBC surface glycoproteins inhibiting complement (for example, Decay Acceleration Factor, DAF, and CD59)56 and masking RBC from recognition by phagocytes (for example, CD4763 and SHPS-164), further compromises RBC biocompatibility.
These adverse effects reduce RBC plasticity and resistance to osmotic and mechanical damage, lead to RBC opsonization by immunoglobulins and complement promoting phagocytosis (opsonization means “coating by compounds appetizing phagocytes”) and directly destroying RBC, which collectively may lead to RBC lysis, aggregation, immune reactions, cellular uptake, adhesion to vascular endothelium and rapid elimination via phagocytosis and entrapment in the microvasculature30,65–67. These adverse effects compromise drug delivery and may cause serious damage typical of intravascular hemolysis, including acute vascular, renal and immune reactions to free hemoglobin, hypoxia and toxic effects of RBC stroma towards RES macrophages68. On the other hand, rapid phagocytosis of altered RBC offers a direct and effective way for intracellular delivery, on a condition that RBC has not been destroyed by complement en route in the circulation.
Major technological advances have been made about a decade ago, i.e., design of devices allowing semi-automatic high-throughput blood filtration and hypotonic dialysis-based encapsulation into human RBC of drugs including steroids dexamethasone (DEX) and prednisolone, as well as oligonucleotides and peptides, producing amounts of loaded RBC sufficient for use in human patients69,70. Based on these developments, several companies embarked on industrial development of scaled-up production of drug-loaded human RBC and currently pursue clinical studies. Below we briefly overview few examples of delivery of specific types of drugs encapsulated in carrier RBC in animal and human studies. Most of these strategies pursue drug delivery to phagocytic cells in blood and RES (first of all hepatic and spleenic macrophages) or prolonged circulation of RBC-encapsulated enzymes detoxifying various toxic substances in the bloodstream (Figure 1).
As expected, modifications that altered RBC surface antigens and membrane plasticity (e.g., treatment with cross-linking agents) resulted in their rapid phagocytosis by macrophages in the RES71,72, providing a mechanism to deliver encapsulated drugs into lysosomes in these and other cell types with active internalization processes including tumor cells26,73 (see section below). Pilot studies showed that microparticles made from RBC ghosts facilitate delivery of cytotoxic agents to malignant cells74.
Genetic deficiency of lysosomal acidic hydrolytic enzymes results in pathological accumulation of their substrates in the cellular vesicles, leading to lysosomal storage disorders, LSD, manifested by inflammation, neurological, vascular, hepatic and pulmonary disorders75. Macrophages and other cells with active lysosomal metabolism represent the prime therapeutic target in LSD management. Pending development of effective and safe gene therapy, the only viable and clinically used option for therapeutic management of LSD is periodical infusion of deficient recombinant enzymes76, i.e., enzyme replacement therapy, ERT77. However, inactivation en route, poor pharmacokinetics and uptake by the target cells compromise this approach: only a minute fraction of these protein drugs get into the lysosomes; hence an acute need in improving delivery using drug carriers78.
Effective uptake and lysosomal addressing of drug-loaded RBC destined for fast phagocytosis due to membrane modification offers a natural mechanism for ERT delivery4,22. In fact, initial studies of RBC as carriers for drug delivery were focused on RBC loading with enzymes for ERT. Hypotonic exchange (i.e., reversible mild poring of RBC membrane in an enzyme suspension) was the most widely accepted and effective among methods for encapsulation in RBC enzymes used as ERT for treatment of Gaucher’s disease including galactosidase8, glucuronidase79 and glucocerebrosidase4,22. Efficacy of enzyme loading was reversely proportional to the molecular weight, yet even 180kD proteins have been encapsulated in RBC using hypotonic exchange8. RBC-encapsulated enzymes showed stable activity22 and delivered enzyme cargoes into cells in vitro4. Animal studies revealed relatively more effective lysosomal delivery of RBC-encapsulated vs. free enzymes, despite (or, perhaps, rather in agreement with) very limited circulating capacity of the former formulation79. Limited clinical studies in late seventies showed no overt toxicity of RBC-encapsulated glucocerebosidase in a patient with advanced adult type of Gaucher’s disease, yet therapeutic effect was rather modest and transient80. More recently, RBC-loaded enzyme replacement therapy using thymidine phosphorylase has been tested in a patient with a genetic mitochondrial deficiency of this enzyme: treatment improved biochemical readouts, but, unfortunately, the patient’s clinical condition did not improve81.
Phagocytosis of RBC intentionally modified in the drug loading process to be taken up by macrophages in the RES serves as a natural delivery path for agents that help to eliminate invaders residing in these cells73,82. For example, anti-viral drug azidothymidine (AZT) was loaded in carrier RBC83 that delivered cargo to macrophages and provided enhanced anti-viral potency vs free drug in cell culture26,84 and in a mouse model of HIV infection85. Encouraging results have been obtained in cells with RBC-mediated delivery of other anti-viral agents86–90 including antisense agents inhibiting HIV-1 replication in infected cells91. These studies provide a basis for a wide-range antiviral strategy87,92,93 posed for systematic testing in animal models and human studies. It has to be noted, however, that loading of some anti-microbial drugs into RBC (i.e., anti-malarial agent clotrimazole) predisposes RBC to oxidative damage59, and oxidized RBC are rapidly taken up by hepatic RES macrophages (i.e., Kupffer cells) via scavenger receptor-mediated phagocytosis94.
Antigen-presenting function of macrophages and other immune cells eliminating altered RBC also offers an attractive natural mechanism for delivery of antigens to boost immune response95. In addition to optimized delivery of antigens, carrier RBC plays a role of the adjuvant, by presenting multiple copies of antigens and stimulating non-specific immune response96. Further, encapsulation of cytokines including interleukins and interferon into RBC facilitates delivery of these agents to macrophages97, resulting in stimulation of immune response in animal models98.
Alternatively, RBC encapsulated with toxic agents, such as ricin toxin kill target cells, first of all, phagocytes99. Injection of a toxin-loaded RBC leads to macrophage depletion100 providing anti-inflammatory effect and alleviation of acute graft injury after transplantation101. In theory, delivery of toxic agents by RBC to immune cells may be used for anti-inflammatory interventions, as well as for induction of antigen tolerance.
Delivery of RBC-loaded anti-inflammatory drugs such as glucocorticoids including dexamethasone (DEX) to pro-inflammatory cells such as macrophages represents further extension of the previous approach. It promises to optimize bioavailability of these poorly soluble drugs and selectivity of their delivery to active phagocytes in the RES and other components of immune system. Initial studies in vitro developed loading of DEX derivatives (e.g., more soluble DEX-phosphate) into RBC; since this procedure predisposes RBC to opsonization by complement facilitating phagocytosis, RBC-loaded DEX was taken up by cultured macrophages and inhibited their pro-inflammatory response to agonists70.
In a recent series of studies by Magnani’s team, this approach is currently being tested in human patients with several disease conditions associated with and aggravated by inflammation. For example, re-infusion of RBC-loaded DEX in ten patients suffering of chronic obstructive pulmonary disease, COPD, has been apparently well tolerated and resulted in a sustained elevation of blood DEX level after a single injection14. In other lung disease with a major inflammatory component, cystic fibrosis, re-infusions in the patients of autologous RBC-loaded DEX at monthly intervals provided sustained low-level of DEX for 28 days in the bloodstream, were well tolerated and provided significant reduction of inflammatory reactions102. Similar approach has been tested in the patients with inflammatory bowel disease (IBD, such as Crohn disease) and in this study three repetitive re-infusions of autologous RBC loaded with DEX (every four weeks) also provided a prolonged elevation of DEX blood level, permitting the patients to withdraw previously prescribed poorly tolerated steroids and still achieve remission that has been maintained for several months103. Similar encouraging results have been observed in a study involving 18 pediatric patients treated with monthly infusions of autologous RBC-loaded DEX for two years104. Finally, a very recent randomized controlled study of this treatment in forty IBD patients refractory to conventional steroids showed that by 8 weeks of treatment 75% of twenty patients that received RBC-loaded DEX were in clinical remission (vs 80% in the group that received prednisolone and 10% in the sham group, respectively), but no adverse effects have been detected in RBC-DEX treated group, in contrast with 80% patients showing adverse effects of prednisolone105. Certainly, number of the patients enrolled in these studies (10–15) was very small on the scale of regular clinical trails. However, these encouraging pilot results imply that RBC-mediated delivery of anti-inflammatory agents may find utility in treatment of acute and chronic inflammation.
Loading anti-cancer drugs into carriers restricts their toxicity to the body and improves their delivery to tumors relies via several mechanisms, both specific (e.g., antibody targeting) and less specific (e.g., Enhanced Permeation and Retention effect, EPR, typical of solid tumors). Liposomes, linear polymers and polymer micelles represent the most popular carriers for anti-cancer drugs. However, RBC carriers may find a niche in tumor treatment, for example, by providing formulations with prolonged circulation. In support of this notion, loading a hydrophobic anti-tumor agent dequalinium into mouse RBC provided much longer half-life in circulation than PEG-liposomal formulation (5–6 days vs 4 hours)106.
Anti-cancer drugs such as antibiotic doxorubicin have been encapsulated into carrier RBC using diverse loading schemas including glutaraldehyde cross-linking of RBC membrane13,107. This modification greatly enhances RBC uptake by macrophages and other cells exerting active phagocytosis71. Accordingly, doxorubicin-loaded RBC delivered the cargo into macrophages in culture108 and accumulated in the liver (predominantly, in macrophages) after intravenous injection in animals including dog109.
This intervention provided encouraging efficacy in treatment of lymphoid tumor in dogs without marked cardiac toxicity (a hallmark adverse effect of doxorubicin), yet inflicted unexpected substantial chronic suppression of myeloid cells110. Nevertheless, a formulation of human autologous RBC encapsulated with a related anthracycline antibiotic daunorubicin prepared using methodology avoiding RBC membrane cross-linking has been injected in patients with acute leukemia and showed a more prolonged drug level in plasma and lesser side effects than after injection of free drug111. Similarly, doxorubicin-loaded autologous RBC re-infused in patients with lymphomas, provided reduction of peak level and extension of drug level in plasma of patients resulting in significant elevation of the area under the curve and reduction of side effects comparing with free drug112.
Delivery of drug carriers to solid tumors relies in major part on the EPR effect mediated by abnormally high permeability of tumor vasculature and lack of effective lymphatic drainage. In the context of vascular permeability and tumor extravasation via EPR effect, large RBC represent less effective delivery platform than sub-micron carriers such as liposomes. In order to address this challenge, anti-tumor drugs (daunorubicin) have been conjugated with small vesicles (average diameter 100 nm) formed from RBC plasma membranes74. Soon after intravenous administration (<30 min) these RBC-based nano-vesicles are eliminated from the circulation mainly by the RES in liver and spleen113. However, injection of this formulation produced more potent anti-tumor effects than free drug in mouse models114, most likely due to slower drug release in the vicinity of tumor cells115, since these vesicles apparently do not enter target cells116.
Finally, RBC ghosts have long been studied as means for intracellular delivery of genetic materials. Most efforts in this area have been focused on cytoplasmic delivery of small oligonucleotides for interference in protein synthesis. Early works demonstrated proof of principle in cell cultures and provided initial comparison of this and liposomal antisense delivery systems44. More recent studies confirmed intracellular delivery of oligonucleotides70 and other means of genetic interference, such as peptide nucleic acid inactivating viral RNA replication in culture of human macrophages infected with HIV91. Several recent studies took this direction into animal studies. Thus, injection of RBC-encapsulated DNA plasmid led to a prolonged (up to 3 days post injection) expression of a transgene in blood mononuclear leukocytes45. Of note, no transgene expression has been reported at this time in organs including hepatic Kupffer cells, which in most animal studies take the lion share of injected materials. The nature of targeting to blood leukocytes vs. RES macrophages indirectly inferred by this outcome remains enigmatic. In contrast, very recent study showed that antisense-loaded RBC getting opsonized in plasma deliver their cargo to the liver, consistently with known destination of RBC to this organ43.
Delivery of RBC-encapsulated drugs discussed above is based on uptake of modified RBC by macrophages, immune and tumor cells. In contrast, in theory, minimally altered RBC loaded with drugs degrading diffusible toxic compounds could circulate for a prolonged time avoiding rapid uptake by RES, thereby providing sustained antidotes to toxins.
Design of non-traumatic loading schemas and use of additional precautions (e.g., elimination of sub-population of senescent RBC from the mixture) yielded formulations of drug-loaded resealed RBC showing biocompatibility and pharmacokinetics similar to those of unloaded RBC in animal studies50,66. This provided marked prolongation of half-life in the bloodstream of RBC-encapsulated agents vs. free counterpart injected via the same route, including alcohol oxidase117, erythropoietin50, carbonic anhydrase30 and other agents30,46. Isotope-loaded RBC have been used to visualize blood pool imaging by gamma-scintigraphy and MRI41.
Loading capacity of RBC is limited; hence, highly potent and specific enzymes represent more effective cargo for this approach than non-enzymatic antidotes such as glutathione118. More than ten different detoxifying enzymes have been encapsulated into carrier RBC to test this hypothesis, including urikase to eliminate uric acid119, thiosulfate-cyanide sulfutransferase (AKA rhodanese) converting cyanides into less toxic thiocyanates120–122, phosphothioesterase to antagonize organo-phosphorus compounds including toxin paraoxon123–125, alcohol oxidase and alcohol dehydrogenase for elimination of methanol and other toxic alcohols117,126,127, L-asparaginase48,49,128, adenosine aminase and other enzymes (Table 2). Derivatives of some of these enzymes modified with polyethylene glycol (PEG-enzymes, partially masked from immune system) have also been encapsulated in mouse, human and sheep RBC129–131.
In most of these studies, encapsulated enzymes retained activity and degraded their substrates in vitro. Studies of circulation, biodistribution and in vivo stability of enzyme-loaded RBC were rather fragmentary and, in many cases, revealed reduction of circulation time comparing with normal RBC132. Nevertheless, even this suboptimal approach afforded more prolonged blood level, as well as more potent and sustained detoxifying effects comparing with a free enzymes including rhodanese132 and alcohol oxidase117. Infusion of RBC-encapsulated phosphotriesterase protected mice against lethal dose of a toxin paraoxon125. In some cases, encapsulation of enzymes with cofactor molecules facilitated substrate influx and enzymatic conversion, e.g., kinetics of RBC-encapsulated rhodanese has been improved by co-loading of organic thiosulfonates122,133. Such binary detoxification system provided significant reduction of cyanide level132 and protected against lethal dose of cyanide in mice134, showing promising efficacy in a mouse model of cyanide poisoning135. Injection of homologous RBC loaded with PEG-urease/PEG-Aldehyde dehydrogenase in sheep provided more prolonged elevation of the enzyme activities in blood than injection of free PEG-modified enzymes (6 vs 2 days, respectively)136.
Several formulations of RBC-encapsulated detoxifying enzymes have been tested in primates and human patients. In an early study, RBC-encapsulated asparaginase showed more prolonged circulation (in the range of several days) and more prolonged reduction of asparagine plasma level than free enzyme injected in monkeys128. In mice, 51Cr-labeled RBC-encapsulated asparaginase circulated as a complex showing the same half-life for RBC carrier and the drug (although it was shorter that half-life of control RBC)137. In humans, pharmacokinetics of RBC-loaded asparaginase showed considerable variability between 13 tested patients, yet provided a significant prolongation of half-life in the plasma vs. free enzyme (27–29 days vs. 8–24 hours, respectively) and a more profound and prolonged reduction of asparagine level in plasma48. Based on this encouraging outcome, Kravtzoff and co-workers have studied tolerance of RBC-asparaginase in human patients and found no overt harmful effects, nor antibodies in plasma after a single injection49. Separation of marginal sub-populations of drug-loaded RBC (e.g., senescent or unintentionally damaged RBC) using gradient centrifugation helped to minimize dosing variability between and within the same batches138. New methods for asparaginase loading into RBC based on enzyme modification by low molecular weight protamine has been recently proposed, yielding formulation with longer half-life in mice than formulation than RBC-loaded asparaginase produced by hypotonic dialysis method and showing promising therapeutic effect in mouse model of leukemia dependent on exogenous asparagine139.
Other detoxifying enzymes encapsulated in carrier RBC include glutamine synthase for ammonia detoxification, providing circulation of detectable enzymatic activity for 48 hours and reduction of ammonium level by 50% in mouse blood140. Alcohol, glutamate and aldehyde dehydrogenases have been encapsulated into mouse RBC with variable yield and high resultant enzymatic activities (e.g., RBC/GDH effectively metabolized high quantities of ammonia) using electroporation127 and hypotonic dialysis141. These loading schemas reduced RBC stability, yet injection of RBC-encapsulated GDH alleviated ammonia toxicity in mice141. Isotope tracing of 51Cr-RBC showed that in contrast to control RBC, a major fraction (>50%) of electroporated RBC with encapsulated dehydrogenases was eliminated from the bloodstream within several hours, yet the kinetics of second phase of RBC/ADH removal was only slightly faster than control RBC (T1/2β approached 4.5 vs 5.3 days, respectively)142.
Native and PEG-modified adenosine deaminase (ADA) has been encapsulated in human RBC to achieve sustainable elimination of non-metabolized deoxiadenosine that accumulates in and inhibit immune cells in the patients with reduced adenosine deaminase level in blood143. Human studies showed that PEG-ADA loaded RBC circulate better than native ADA-loaded RBC, although both formulations have a fairly short half-life (20 vs. 12 days, respectively, which still was longer than that of PEG-ADA itself, 3–6 days)47. Clinical studies performed by this group involve very limited numbers of patients (1–2 per study), yet in a recent publication they have reported a patient that has been treated by RBC-loaded PEG-ADA for correction of a genetic deficiency for nine years with total 225 infusions every 2–3 weeks without overt adverse effects and with significant, although transient, improvement in lymphocyte numbers, sustained level of blood ADA activity and immunoglobulin level, and clinical improvements144.
Coupling therapeutics to the surface of carrier RBC represents an alternative to encapsulation strategies that have been considered above. RBC membrane provides an extended surface area that may be used for anchoring multiple copies of protein or other therapeutic molecules. Lack of isolation of a drug from blood en route to the therapeutic site represents an obvious downside of surface coupling vs encapsulation. This concern, however, does not seem acute for drugs that are supposed to work in the bloodstream. Furthermore, using pro-drug formulations resistant to plasma inhibitors holds a promise to resolve issues associated with premature inactivation and side effects en route. On the other hand, surface coupling strategies avoid damaging encapsulation procedures and therefore offer theoretical advantages of drug loading without compromising RBC biocompatibility. In addition, coupling of drugs to RBC surface circumvents issues related to drug release (approaches to trigger drug release by using controlled lysis by complement have been suggested, yet practically useful controlled release from carrier RBC remains an elusive goal)28. Of note, coupling to RBC surface resolves diffusional limitations: even enzymes that react with small, membrane permeable substrate are more active when bound to the RBC surface than when incorporated within the cell145. Further, surface coupling offers a unique option to load drugs on circulating RBC without technically and logistically cumbersome need for their extraction necessary for drug encapsulation and re-infusion.
Generally speaking, techniques for coupling diverse molecules to RBC have been designed in the fifties, in the process of development of reagents for immunological reactions of agglutination. Numerous cross-linking agents and procedures have been applied to conjugate proteins and other antigens and biological molecules to RBC of different animal species including humans. Subsequent studies revealed that these conjugation methods grossly damage RBC membrane, reducing RBC plasticity, resistance to lytic agents and biocompatibility. Nevertheless, reliable methods of biocompatible conjugation molecules to RBC have been designed recently (see below).
A theoretical paper of mid-nineties provided a speculative yet stimulating analysis of hypothetical RBC membrane anchors and methods of coupling of therapeutics using chemical conjugation to tentative affinity ligands and gave few examples of experimental studies in this area, available at the time20. Several practical strategies for coupling therapeutics to carrier RBC surface have evolved and have been tested in vitro and in vivo in last two decades. These strategies can be divided into three wide categories, described in further details in the following sections: i) chemical coupling of agents to RBC surface (either covalent, or non-covalent); ii) coupling to RBC membrane of a receptor that binds a therapeutic agent (and, in some cases, augments its functions); and, iii) conjugation of therapeutics or their receptors with affinity ligands (e.g., antibodies or their fragments) that bind to RBC thereby anchoring cargoes on RBC (Figure 2). This is the latter strategy that permits loading drugs on RBC surface by injecting these conjugates into the bloodstream. Both these strategies provide coupling of antibodies, antigens, enzymes, cytokines and other biologically active cargoes to RBC and are been explored for vascular delivery of several classes of therapeutics including, more recently, model polymer nanocarriers anchored to RBC either non-specifically146,147 or via affinity peptides148. Below we consider surface coupling to RBC for delivery of the following classes of biotherapeutics: i) antibodies and antigens; ii) affinity ligands for coupling and elimination circulating pathogens; iii) proteins regulating complement system; and, iv) proteins controlling formation and dissolution of blood clots.
In theory, RBC carrying antibodies or antigens on their surface can be employed to deliver diverse cargoes to intravascular targets149 or agents modulating immune response95, respectively. Since early eighties, many methods have been tested for coupling protein molecules to RBC for in vitro applications including use of non-specific chemical cross-linkers such as tannic acid150 and chromium chloride151,152. These methods have been surpassed by more specific cross-linkers, e.g., biotin-avidin pair offering modular anchoring of diverse biotinylated chemicals including proteins and nucleic acids to defined reactive groups on RBC membrane, i.e., amino acids153–155, sulfhydryl groups156, sugars157 and lipids158,159. In particular, controlled biotinylation of RBC lysine residues using NHS esters of biotin become arguably one of the most popular means for conjugation cargoes to RBC surface for a wide variety of applications in vitro and in vivo69,160–164.
One of such applications, namely, isolation and tracing of subpopulations of RBC in circulation165,166 as well as monitoring their survival167 and volume168, had found use in animal169,170 and human studies involving injection of normal, senescent and sickle-cell biotinylated RBC171,172. Furthermore, methods for direct biotinylation of RBC in the bloodstream using intravascular injection of biotin esters have been explored170,173 (this method likely yielded promiscuous modification of diverse blood cells and endothelium). On a cautionary note, an excessive biotinylation may reduce RBC biocompatibility, alter RBC antigens164 and repetitive injections of biotinylated RBC elicit immune response174. It has also been found in late eighties that excessive cross-linking of biotinylated RBC membrane by avidin, streptavidin or neutravidin, all of which have four high-affinity binding sites for biotin and thereby serve for coupling biotinylated molecules to RBC, causes to RBC lysis by complement activated via the alternative pathway27,175, leading to intravascular hemolysis and rapid elimination of modified RBC176. Studies of the molecular mechanisms of this phenomenon revealed that modification of RBC membrane glycoproteins Decay Acceleration Factor (DAF) and CD59 (that suppress complement activation and assembly of membrane-attacking complex in RBC membrane, respectively), is responsible for this unwanted side effect56,177,178. This allowed design of non-damaging means for coupling of molecules to RBC via biotin-avidin cross-linker without loss of RBC biocompatibility159,179; thus RBC carrying up to 105 molecules of protein cargo conjugated via streptavidin in a biocompatible manner circulate in animals similarly to naïve RBC, without enhanced clearance, lysis or organ uptake180,181.
Several labs explored use of RBC coated with antigens and cytokines for stimulation of immune response in vitro182,183 and, at more limited scale, in vivo184. Antibody-guided RBC formulations have also been tested for delivery to populations of lymphocytes to achieve selective modulation of immune response152,185. Further, model studies demonstrating proof of principle for targeting antibody-carrying RBC to selected sites in the vasculature have also been published3,149,151. However, use of antibody-coated RBC for targeted drug delivery in the vascular system has not been actively pursued in the last decade. The need for ex vivo modification of RBC for antibody conjugation and drug loading, as well as lack of practically adequate means for controlled release of drugs encapsulated into the carrier RBC represented a daunting technical challenge. In addition, safety issues associated with hemotransfusion inevitably involved in this strategy were viewed unfavorably by industrial sector in the age of burst of HIV and other blood transmitted infections. As a result, synthetic carriers including liposomes and polymer particles surpassed drug targeting strategies using antibody-carrying RBC.
Conjugation of highly hydrophilic polyethylene glycol (PEG) with the chain length in the range MW 3–10kD has evolved since seventies as a universal “stealth” technology, prolonging circulation and masking from defense systems in the body of liposomes, polymer nanocarriers, proteins and other drug carriers and drugs themselves. The goal of producing PEG-ylated “stealth” RBC, proposed by Scott and co-authors a decade ago, is to obtain a ‘universal” donor blood for hemotransfusion by chemically camouflaging RBC antigens186–188. Indeed, PEG-coated RBC are less effectively opsonized, taken up by phagocytes and recognized by antibodies to RBC antigens189–191. Masking against immune reaction to mismatched ABO antigens is the most challenging goal; in this setting, PEG-coating offered no protection and rather aggravated hemolysis in the initial studies191. Additional studies using alternative PEG-coupling techniques and combinations of PEG with different chain length produced encouraging results in masking ABO and Rh(D) blood group antigens192–194. More recently, even masking of xeno-antigens on RBC has been attempted, yet the outcome was not too encouraging195.
Covalent coupling of cyanuric chloride activated PEG derivatives to amino acids is the most popular method for PEG conjugation to RBC191,196. PEG coupling using sulfo-group chemistry192,194, insertion of lipid derivatives of PEG197 and other methods have also been developed186,198,199. Extent of “stealth” feature or masking increases proportionally to PEG length in the range 5–35 kD, branching and surface density200. Studies of RBC electrophoresis showed that PEG conjugation increases apparent length and density of RBC glycocalyx201 and that long and especially branched PEG polymers work more effectively in this respect202. Similar results have been obtained when RBC was modified by Pluronic, a tri-block copolymer combining two PEG chains at the ends of a less hydrophilic moiety203. Of note, RBC modification using PEG length and surface density that does not mask complement receptor CR1 against antibodies, profoundly decreased binding of immune complexes to RBC, indicating that even relatively small steric hindrance may obstruct multivalent interactions of immune complexes with CR1204. This observation is important in the context of strategies for CR1-mediated clearance of pathogens discussed below.
PEG-modification at the extent that effectively masks RBC from recognition by immune system affects neither functions of RBC membrane glycoproteins (e.g., ion exchange function of Band 3), nor RBC stability, plasticity and biocompatibility190. Thus, PEG-RBC circulate with half-life similar to that of non-modified RBC in syngenic animals186,190. Additional fractionation of PEG-coated RBC provides the PEG-RBC sub-population that is most effectively masked, less damaged and circulates equally to native RBC205. Furthermore, PEG-coated RBC are less susceptible to parasite infection including malaria Plasmodium,206 due to masking their receptors196. In addition, PEG-modified RBC demonstrate reduced tendency to aggregation203,207 and improved rheological properties: reduced low shear flow viscosity189 and enhanced thickness of membrane protective layer and plasticity necessary to endure hydrodynamic stress in circulation196,208,209. In the last decade, PEG-RBC is an active area of research promising to alleviate acute problems of shortage of matched donor blood (see reviews by Garratti on this subject)210,211.
It has been found several decades ago that one of RBC transmembrane glycoproteins, Complement Receptor Type 1 (CR1), binds C3b component of activated complement and immune complexes containing this protein and that macrophages in the RES safely detach such immune complexes including antibody-pathogen complexes from circulating RBC without damaging the cell212. Two decades ago, Ron Taylor postulated that this natural function, i.e., immune clearance of pathogens from the bloodstream, can be performed as a controlled medical procedure that would not require complement activation, by injecting artificial immune complexes called heteropolymers that consist of a monoclonal antibody to CR1 conjugated with an antibody to a pathogen or toxin213. This strategy has been emulated later by a strategy for a decoy-type clearance of HIV-1 by RBC carrying electro-inserted CD4 in their plasma membrane that showed initial promise in vitro studies employing cell cultures of blood mononuclear cells from HIV-1 patients214.
In primates and humans, >90% of CR1 is expressed on RBC at levels of ~500–1,500 copies per cell, providing an anchorage site for CR1 antibodies and compounds conjugated with anti-CR1 (i.e., heteropolymers) injected in blood215–218. Loading of such heteropolymers on RBC provided effective binding of model antigens and bacteria in vitro213,219,220 and in non-human primates221 (of note, rodents do not express CR1, hence all in vivo studies of CR1-mediated blood clearance have been performed in monkeys until recent production of a transgenic mouse expressing human CR1222). CR1 represents an immunologically privileged site for antibody binding to RBC: isotope tracing and fluorescent imaging studies revealed that binding of neither anti-CR1 nor anti-CR1 conjugates targets carrier RBC for phagocytosis223, yet phagocytes recognize pathogens and immune complexes bound to CR1 either via C3b or anti-CR1224, cleave off extracellular domain of CR1225 and take up the pathological “cargo” from RBC surface226–228. Studies in primates demonstrate that diverse ligands can be coupled to circulating RBC using anti-CR1 conjugates and eliminated by phagocytes without damage or shortening RBC survival213,215,229,230.
This concept has been tested in primates and showed promising effectiveness of elimination of diverse bacterial231 and viral232–235 pathogens using CR1 heteropolymers targeted to these pathogens, thereby alleviating the infection235,236. Further, coupling to RBC of anti-CR1 conjugated with DNA, a common antigen for auto-antibodies in lupus afforded clearance of such auto-antibodies in monkeys230,237,238; the same principle of CR1-targeted heteropolymers has also been explored for elimination of cytokines as anti-inflammatory intervention239, indicating potentially wide biomedical application of this concept215.
Complement system, consisting in more than 20 regulatory and executing proteins in blood plasma and cellular membranes, exerts key functions of innate immunity including opsonization and destruction of pathogens, tumor and foreign cells, and activation of pro-inflammatory cascades in the sites of invasion. However, in some pathological conditions, host cells suffer injury inflicted by overzealous or misguided activation of complement. Vascular endothelium and RBC represent the most common and vulnerable target for adverse effects of autologous complement activation, especially in situations of functional deficiency of membrane glycoproteins inhibiting complement: Decay Acceleration Factor (CD55 or DAF), CD59 and CR1 (CD 35, represented in mice by an analogue called Crry). DAF and CR1 inhibit early stages of complement activation, thereby protecting cells from lysis and reducing generation of pro-inflammatory mediators, whereas CD59 blocks formation of hemolytic pores in the plasmalemma. Complement-mediated hemolysis of RBC deficient in DAF and CD59 is involved in mechanism of paroxysmal nocturnal hemoglobinuria (PNH), whereas endothelial damage by complement is involved in acute vascular injury in ischemia-reperfusion syndrome, such as happens in organ transplantation.
Several groups pursued targeting complement inhibitors to RBC, to protect them from hemolysis and inhibit complement activation. Of note, natural DAF and CD59 are anchored on the luminal surface of RBC membrane via a lipid anchor, glycosylphosphatidylinositol (GPI). Accordingly, experimental methods for insertion of DAF, CD59 and other GPI-linked proteins into RBC plasmalemma using the lipid anchor have been designed240,241. Insertion of lipid-anchored CD59 in RBC plasmalemma protects against complement-mediated hemolysis242, providing a proof of principle for new approach for PNH therapy.
The plasma membrane domains that harbor artificially inserted GPI-linked proteins are not fully elucidated243, yet they differ from cholesterol-rich domains that tightly retain natural GPI-anchored proteins244. As a result, GPI-anchored proteins artificially inserted in membrane (“painted”) more easily release from RBC241. Perhaps, this is one of the reasons why RBC transfer artificially “painted” GPI-linked proteins to other cells in vitro245 and in vivo, where endothelium represents the preferential acceptor of GPI-inserted proteins from RBC246. As a result, injection of RBC carrying GPI-linked DAF and CD59 artificially inserted using gene therapy means alleviates acute ischemia-reperfusion injury in swine-to-primate model of xenograft transplantation247.
Of note, chemical conjugation to RBC plasmalemma is undesirable for coupling of complement inhibitors, because this approach would make coupling irreversible, which is not desirable for protein transfer from RBC to endothelium. In addition, it would require RBC isolation, modification and re-infusion, which inevitably reduce practical utility of the approach and RBC resistance to complement. Conjugation with antibodies also represents suboptimal mean for binding complement-regulating proteins to RBC, since cross-linking RBC membrane by multivalent conjugates can damage RBC. From the standpoint of safety, as well as industrial and clinical translation, small monovalent antigen-binding fragments of antibodies, i.e., recombinant single chain variable fragments (scFv) represent the preferable targeting moiety. Using modular gene engineering biotechnology methods, these recombinant proteins can be fused via short connecting peptides with variety of executing proteins. Thus recombinant scFv-fusions targeted to RBC hold promise to provide a series of clinically useful for loading biotherapeutics onto circulating RBC without need for RBC isolation, modification and hemotransfusion.
Expression of scFv in diverse vectors enables large-scale, GMP-quality production of homogeneous monovalent scFv/PA fusion proteins248,249. Advantages of scFv include: i) Lack of Fc-mediated side effects; ii) Lack of cross-linking of anchoring sites on RBC and RBC aggregation; iii) Due to its smaller size (~50 kDa), scFv/PA can be injected intramuscularly, as other recombinant protein therapies (e.g., insulin); iv) Established techniques for humanization and reduction of immunogenicity of scFv further help to minimize the likelihood of eliciting immune reactions; v) Modular recombinant format of scFv fusion supports synthesis of diverse fusions250.
For example, a recombinant fusion protein combining scFv directed to Rh(D) blood group antigen with human CR1 binds to CR1-deficient RBC and restores RBC ability to bind immune complexes251. This in vitro study implies that this approach may eventually be used to either replenish CR1 functions (i.e., immune clearance and complement inhibition) in CR1-deficient patients (~10% of humans are CR1-negative), or employed to boost CR1 immune clearance in a manner performed by heteropolymers described in the previous section. Recently, Spitzer, Atkinson and co-workers produced a scFv of a monoclonal antibody TER-119 recognizing a mouse analogue of human glycophorin A252 (GPA), fused it with DAF253 and Crry254 and demonstrated that this monovalent fusion constructs bind to RBC after intravascular injection in mice without damaging RBC, and, furthermore, enhance RBC resistance to lysis by complement in vivo253,254. Furthermore, recently this team performed a neonatal in vivo gene transfer of TER-119 scFv/Crry in mice using retroviral gene transfer vector and demonstrated that prolonged synthesis of this fusion protein in mice leading to its sustained coupling to circulating RBC, restores protection against excessive complement lysis in mice genetically deficient mice255. These studies, showing proof of principle for in vivo delivery to RBC of therapeutic fusion proteins (injected or encoded by gene therapy means) opens exciting applications, some of which will be discussed in the next section.
An idea of intravascular delivery of agents controlling blood clotting and clot dissolution using carrier RBC has been proposed a quarter of century ago, as illustrated by an early work reporting conjugation of fibrinolytic drug streptokinase to RBC targeted to collagen, a thrombogenic component of extracellular matrix that gets exposed to blood in sites of vascular injury3. In theory, coupling drugs to RBC surface may favorably alter their pharmacokinetics (i.e., prolong life-time in circulation) and optimize interaction with components of blood coagulation and fibrinolytic systems accessible from RBC surface. Attempts in this direction included conjugation of heparin to RBC to enhance potency of anticoagulant thromboprophylaxis in patients predisposed to thrombosis256 and conjugation of pro-thrombotic RGD-containing peptide to RBC to design a substitute for platelet infusion in patients predisposed to hemorrhagic disorders.27
RBC carrying conjugated drugs reported in these studies exerted good functional activities in vitro2,3,256. However, until recently, no attempts to test these drug delivery systems in animal models have been reported, presumably because conjugation of drugs grossly compromised RBC biocompatibility. In particular, inactivation of complement inhibitors DAF and CD59 in RBC membrane257 led to hemolysis, phagocytosis and rapid elimination of RBC27,175–178,258. Eventually, methods to couple up to ~105 copies of therapeutic proteins per RBC without RBC damage have been devised.150,159,163,179,180 In vivo studies using radioisotope tracing showed that 51Cr-RBC/125I-drug complexes circulate similarly to control RBC for several days after injection in rats259 and mice180,181. This success brought back on the agenda attempts to couple fibrinolytic agents to RBC and test benefit/risk ratio of this approach in animal models of thrombosis.
Sealing of damaged blood vessels by mural clots prevents bleeding, while pathological vessel occlusion by intravascular clots (thrombosis) causes tissue ischemia and damage, leading to acute myocardial infarction (AMI), ischemic stroke, pulmonary embolism and peripheral vascular disease, among other complications. Thrombosis is the leading cause of mortality and disability in the US260,261. Of note, thrombi are prone to recur within hours to days after an AMI or stroke and the risk is great after transient ischemic attack or pulmonary embolism and in immobilized patients262–265. Thrombosis and embolism are also a common and dangerous complication of surgery that is especially difficult to manage due to the risk of acute bleeding at the operative site. Invasive interventions (e.g., angioplasty, carotid endarterectomy) may be complicated by formation of clots that embolize to the brain and cause neurological disorders. Thus, situations in which patients are at highest short-term risk for occurrence or recurrence of thrombosis are known. However, anti-platelet and anticoagulant agents provide limited protection and pose considerable risk of bleeding266–269, especially soon after the surgery; in addition some anticoagulants (e.g., Warfarin) require many hours to develop an effect, which is inadequate for acute short-term thromboprophylaxis.
Emergency therapy of thrombosis employs injection of plasminogen activators including tissue type (tPA) and urokinase (uPA), middle-size proteases (MW 30–60 kD) that generate plasmin, which cleave fibrin clots and thus restore perfusion249,270. However, inadequate delivery (blood clearance within <15 min271), inactivation by plasma inhibitors such as PAI-1272 and impermeability of occlusive clots273 restrict the effectiveness of therapeutic fibrinolysis by PA. Within minutes after infusion of mega-doses of fibrinolytics (e.g., ~100 mg of tPA) needed to overcome its inefficiency and achieve fibrinolysis locally, excess drug diffuses into pre-existing hemostatic mural clots predisposing to bleeding and into tissues such as the CNS274, where it may cause cerebral hemorrhage, damage to the blood-brain barrier (BBB) and toxicity within the brain275. Due to the danger of bleeding and the collateral CNS damage, fibrinolytics cannot be used in over 95% of stroke patients and in the post-operative period other than as an emergent potentially life-saving intervention. A more ideal thromboprophylactic agent would prevent occlusive thrombi from forming without lysing hemostatic mural (e.g., post-surgical) clots and causing extravascular toxicity.
Attempts to improve tPA delivery and its benefit/risk ratio have not yielded decisively better outcomes276–279. Ironically, the higher affinity of newly developed PA variants for clots promotes drug retention on the clot surface, impeding permeation into the occluding thrombi. The only currently employed use of tPA, i.e., post-thrombosis, is also marred by inevitable delays (time needed for diagnosis, injection and the lysis proper, slowed by clot impermeability), increasing the risk of ischemia-reperfusion (I/R) injury that worsens outcome. Prophylactic delivery of a fibrinolytic into the interior of growing, early nascent thrombi will arrest clot propagation and cause rapid clot lysis. Lysis of clots from within will be more homogeneous and complete than “therapeutic” external fibrinolysis from the clot surface. This would minimize the incidence of the secondary embolism and re-thrombosis. Prophylactic use of tPA in patients at high risk of imminent primary or recurrent thrombosis will lessen the formation of impermeable occlusive clots due to delays in fibrinolysis. However, fibrinolytics are not used for prophylaxis due to their rapid clearance and side effects. Newly designed mutant plasminogen activators with enhanced potency and fewer side effects may improve therapy279–284, but their diffusion into occluding clots has yet to be tested and no fibrinolytic has been designed for prophylactic use. All existing plasminogen activators are short-lived (<30 min, insufficient for prophylaxis) and small (<10 nm) agents, capable of diffusing into hemostatic clots (bleeding) and into the CNS (collateral damage). None is suited for use as prophylaxis in post-surgical or other patients at imminent risk of thrombosis.
Recent animal studies showed that biocompatible coupling to RBC converts plasminogen activators from problematic therapeutic agents into effective and safe agents for intravascular thromboprophylaxis. Hemodynamic factors are favorable, propelling RBC towards the blood mainstream285–287, restricting drug contact with vascular walls and mural clots. Infusion of RBC/tPA complex in rats and mice:
Furthermore, most recent animal studies showed that RBC/tPA provides effective and safe thromboprophylaxis in the most challenging and dangerous vascular bed, i.e., cerebral circulation, thereby preventing deleterious consequences of brain ischemia and stroke in mice293. This study showed that prophylactic RBC/tPA injection in mice provides dissolution of subsequently formed occlusive cerebrovascular thrombi, leading to rapid and stable reperfusion, marked alleviation of ischemic brain injury and improved survival, not attainable by even 10-fold higher doses of soluble tPA (which in fact greatly enhanced mortality). Of note, in contrast with free tPA, RBC/tPA did not aggravate brain edema, injury and hemorrhage in mice with cerebral ischemia and a rat models of post-thrombotic intracranial hemorrhage. Moreover, either prophylactic or post-insult injection of RBC/tPA attenuated disorders of vascular regulation and CNS tissue injury in the brain of pigs subjected to global ischemia/hypoxia, whereas free tPA grossly aggravated these pathological changes294.
Encouraging outcomes of animal studies using injection of RBC/tPA complexes preformed ex vivo using chemical cross-linking pawed the way for most recent attempts to further advance coupling techniques. Thus, in addition to coupling to RBC via streptavidin cross-linker employed as a prototype method in all previous studies of RBC/tPA, urokinase has been coupled to RBC via urokinase receptor chemically conjugated to RBC without loss of biocompatibility295. This approach reduced undesirable interactions of urokinase with its vascular receptors and allowed trigger fibrinolysis, since interaction with RBC-coupled receptor activated urokinase295.
Preformed RBC/tPA conjugates have properties suitable for prophylactic use in settings where transfusion is common, but would be less practical in other settings and challenging to develop commercially. To avoid the need to couple tPA to isolated RBC ex vivo followed by transfusion, designed ways to target tPA to circulating RBC directly have also been designed. Figure 3 illustrates this strategy for coupling plasminogen activators to carrier RBC.
The first approach capitalized on CR1 anchoring strategy, since agents conjugated with monoclonal antibodies to complement receptor-1 (CR1)296 bind to circulating RBC after iv injection in animals including primates, circulate with RBC and bind ligands in vivo without RBC damage213,221,297. Animal studies showed that tPA conjugated to a CR1 monoclonal antibody binds without harm to circulating RBC in mice and affords safe and effective prophylactic thrombolysis289 comparable to that provided by infusion of RBC/tPA288. To alleviate challenges associated with translation and application of chemically produced antibody/tPA conjugates and achieve predictable loading of RBC over a wide range of drug concentrations, a novel recombinant tPA mutant fused to an antigen-binding single chain variable fragment (scFv) of TER-119 monoclonal antibody to glycophorin A (anti-GPA scFv)298,299 has been very recently designed; pilot animal studies showed that this approach allows to load up to 20,000 copies of anti-GPA scFv/tPA fusion per RBC after a single intravenous injection of the fusion without detectable changes in behavior of circulating RBC. On an encouraging note, injection of scFv/tPA in mice provided swift dissolution of subsequently formed intravascular clots, which were impervious to injections of equimolar doses of soluble tPA (Zaitsev et al, JPET 2009, under revision).
Erythrocytes represent a unique and promising, yet somewhat underdeveloped platform for drug delivery. After initial burst of interest and research efforts three decades age, drug delivery by RBC was overshadowed by artificial carriers offering wider range of applications, as well as better control over formulation, storage and utilization of drug delivery system than original RBC-based concepts. Thus, RBC is a good carrier for drug delivery to intravascular and RES targets, but many other important therapeutic targets (e.g., solid tumors, extravascular tissue components, CNS) are normally inaccessible to RBC. Since drug delivery field has been originated and developed predominantly in the context of targeted delivery of toxic anti-cancer drugs, such limitation of the spectrum of suitable targets RBC negatively impacted development of this drug delivery platform.
Studies of RBC drug delivery logically started with in vitro experimentation using isolated RBC and within two decades progressed to extensive animal studies, a necessary step for validation of the viability, efficacy and safety of this drug delivery system, including immune response to RBC-coupled proteins in settings similar to immunization procedures. Of course, certain specific aspects of the RBC drug delivery (e.g., immune response, subtle effects in the CNS and tolerability of RBC/drug complexes by specific patient populations) can be addressed only in clinical studies. The fact that several clinical trials of RBC drug delivery systems have recently been initiated instills a hope that these translational barriers will be eventually overcome.
Among potentially useful biomedical applications, RBC-mediated intracellular delivery of drugs including replacement therapies, imaging probes and toxic agents into RES macrophages and other cells exerting robust endocytic uptake seems as a reasonably promising goal. Delivery of anti-microbial, immunogenic or toxic agents into defense cells can be used for eradication of intracellular parasites, stimulation or suppression of immune reactions, respectively. It remains to be better understood, however, which particular advantages are offered by RBC in this context vs other drug delivery systems, all of which are effectively taken up by RES macrophages and other defense cells (it is more difficult to avoid this addressing). Further, in order to translate this concept into the clinical domain, we must more fully understand and optimize mechanisms of action of RBC-loaded drugs. The pharmacokinetics, stability and rate of release of drugs in plasma have to be systematically characterized and effects on diverse populations of cells in the body defined. This drug delivery system is also a bit promiscuous in terms of selectivity of targeting: many cell types in the body can take up RBC and their remnants. For example, phagocytes, immune and tumor cells all may be targets of antibiotic-loaded RBC. It is conceivable that more precise targeting towards some of these populations may greatly optimize therapeutic effect. It would be undesirable, however, if efforts in this direction would provide very complex, difficult to produce and utilize in medical practice formulations (to be fair, this concern is generally applicable to most of previous and current drug delivery carriers).
Strategies using RBC carriage to augment systemic effects of drugs in circulation such as sustained effects of detoxifying enzymes require no targeting and represent one of the unique areas of RBC drug delivery that offers clear potential advantages over other carriers, due to unique longevity of RBC. Maintenance of maximal biocompatibility of loaded RBC, yield of enzymes loading and kinetics of trans-membrane transport of their substrates and products, as well controlled release and metabolism of encapsulated cargoes represent challenging, yet theoretically surmountable aspects of this approach.
The need for ex-vivo manipulations with RBC, a relatively limited shelf-life and concerns related to the safety of donors matching and blood-born infections are recognized potential downsides of carriage drugs attained by ex vivo RBC loading and re-infusion. These concerns are shared by all types of hemotransfusion, cell replacement and stem cell therapies. Of note, transfusion of blood and blood products is a very widely used and generally safe therapeutic intervention worldwide, the safest and most effective type of cell transplantation strategy. Use of autologous blood (re-infusion) minimizes the safety concerns.
Drug delivery systems targeted to anchor molecules on RBC surface (e.g., scFv-fusion proteins) and therefore allowing safe and technically simple loading of circulating RBC hold a promise to completely solve this issue and greatly expand general applicability of RBC carriers in medicine. In particular, design of intravascular drug delivery platforms using coupling to circulating RBC agents that control immune system, eliminate pathogens and toxins from the bloodstream and correct pathological aspects of thrombosis and hemostasis seem most exciting and unique utilities of RBC drug delivery, promising timely translation into the industrial development and clinical practice.
RBC is naturally designed as a biocompatible carrier for vascular drug delivery, with prolonged life-time in circulation and safe mechanisms for eventual elimination including fixation of complement and uptake by macrophages. Drug encapsulation into RBC and coupling to RBC surface represent two approaches for RBC drug delivery.
Drugs can be encapsulated into isolated RBC using methods including hypotonic dialysis and resealing. RBC-encapsulated drugs are separated from blood, but can exert their activities in circulation if they or their substrates diffuse through RBC membrane. Unintentional damage to RBC in course of encapsulation compromises their biocompatibility and negatively impacts drug delivery except cases when macrophages are the target. Undamaging methods for RBC encapsulation provide clinically testable drug delivery systems that markedly prolong circulation time, bioavailability and effect of cargoes. Delivery RBC-encapsulated anti-inflammatory drugs into phagocytic cells and enhanced bioavailability of detoxifying enzymes in the bloodstream represent attractive examples of this strategy.
Drugs can be coupled to RBC surface using variety of covalent and non-covalent cross-linkers, as well as anchored onto circulating naïve RBC using recombinant fusion proteins with specific affinity to RBC. Animal studies show that surface coupling to RBC can be used for improvement of antigen delivery, masking of RBC antigens, clearance of pathogens from blood and intravascular delivery of therapeutics that suppose to act within the vascular lumen. In particular, coupling of fibrinolytic plasminogen activators to RBC provides the basis for a paradigm-shifting prophylactic thrombolysis, an approach that showed very promising results in animal models of peripheral, pulmonary and cerebral thromboses.
RBC represents a versatile, safe and widely useful carrier for optimization of drug delivery in the vascular system. Several RBC-drug delivery strategies are posed for the translation into industrial development and clinical testing and use.
This work has been partially supported by NIH RO1 HL090697. Author thanks Dr. Juan-Carlos Murciano for help in preparation of the figures.
Declaration of interest:
The author states no conflicts of interest and has received no payment in the preparation of this manuscript.