Messenger RNA (mRNA) has emerged as a new category of therapeutic agent to prevent and treat various diseases. To function in vivo, mRNA requires safe, effective and stable delivery systems that protect the nucleic acid from degradation and that allow cellular uptake and mRNA release. Lipid nanoparticles have successfully entered the clinic for the delivery of mRNA; in particular, lipid nanoparticle–mRNA vaccines are now in clinical use against coronavirus disease 2019 (COVID-19), which marks a milestone for mRNA therapeutics. In this Review, we discuss the design of lipid nanoparticles for mRNA delivery and examine physiological barriers and possible administration routes for lipid nanoparticle–mRNA systems. We then consider key points for the clinical translation of lipid nanoparticle–mRNA formulations, including good manufacturing practice, stability, storage and safety, and highlight preclinical and clinical studies of lipid nanoparticle–mRNA therapeutics for infectious diseases, cancer and genetic disorders. Finally, we give an outlook to future possibilities and remaining challenges for this promising technology.
Messenger RNA (mRNA), which was discovered by pioneering studies in 1947–1961 (ref.1), is a transient intermediator between genes and proteins. By the late 1980s, investigations of mRNA structure and function resulted in the development of in vitro-transcribed (IVT) mRNA2. Since the first proof-of-concept animal study in 1990 (ref.3), numerous strategies have been explored to ameliorate the instability and immunogenicity of IVT mRNA2,4. Additionally, advances in drug delivery systems have expedited the preclinical development of mRNA therapeutics5,6,7,8,9,10,11,12,13,14,15,16,17, providing the basis for mRNA as a new class of drug (Fig. 1).
mRNA has shown therapeutic potential in a range of applications, including viral vaccines, protein replacement therapies, cancer immunotherapies, cellular reprogramming and genome editing2,4,7,8,9,10,11,12,13,14,15,16,17. To achieve therapeutic effects, mRNA molecules have to reach specific target cells and produce sufficient proteins of interest. However, targeted delivery and endosomal escape remain challenging for mRNA delivery systems, highlighting the need for safe and effective mRNA delivery materials.
A variety of materials have been developed for mRNA delivery, including lipids, lipid-like materials, polymers and protein derivatives7,8,9,10,11,12,13,14,15,16,17. In particular, lipid nanoparticles have been thoroughly investigated and successfully entered the clinic for the delivery of small molecules18, siRNA drugs18 and mRNA19,20,21. Notably, two authorized coronavirus disease 2019 (COVID-19) vaccines, mRNA-1273 (refs19,20) and BNT162b21, use lipid nanoparticles to deliver antigen mRNA. Many other lipid nanoparticle–mRNA formulations have been developed and are under clinical evaluation for the prevention and treatment of virus infections, cancer and genetic diseases7,8,9,10,11,12,13,14,15,16,17 (Tables 1,2).
In this Review, we briefly overview representative lipid nanoparticles used for mRNA delivery and describe key steps in the preclinical development of lipid nanoparticle–mRNA formulations, including the overcoming of physiological barriers, different administration routes, manufacturing and safety profiles. Finally, we highlight important examples of lipid nanoparticle–mRNA formulations in clinical studies and provide future perspectives for lipid nanoparticles and mRNA therapeutics.
Development of lipids for mRNA delivery
In 1976, nucleic acids were encapsulated and delivered in polymeric particles5. Later, exogenous mRNA delivery into host cells was demonstrated with liposomes22,23 (Fig. 1). Lipids are amphiphilic molecules that contain three domains: a polar head group, a hydrophobic tail region and a linker between the two domains. Cationic lipids, ionizable lipids and other types of lipid have been explored for mRNA delivery (Fig. 2).
Cationic lipids have a head group with permanent positive charges11,14. For example, 1,2-di-O-octadecenyl-3-trimethylammonium-propane (DOTMA), a quaternary ammonium lipid, has been applied for mRNA delivery in multiple cell types24, and was commercialized as Lipofectin in combination with 1,2-dioleoyl-sn-glycero-3-phosphoethanolamine (DOPE)24. 1,2-dioleoyl-3-trimethylammonium-propane (DOTAP), a biodegradable analogue of DOTMA, was also studied for mRNA delivery25, and is part of the commercial agent MegaFectin, together with DOPE or cholesterol. DOTMA and DOTAP have both been applied either alone or combined with other materials for mRNA delivery7,8,9,10,11,12,13,14,15,16,17; for example, spleen-targeted DOTMA–mRNA lipoplexes (RNA-LPX) have been developed as systemic cancer vaccine26. The same formulation has also been designed as mRNA vaccine for the treatment of autoimmune encephalomyelitis27. This vaccine induces the proliferation of antigen-specific CD4+ regulatory T cells, leading to enhanced immunosuppression and a reduction of clinical symptoms in mouse models27. DOTAP-based cationic nanoemulsions can deliver antigen mRNA against viral, bacterial and parasitic infections28,29,30,31. Moreover, DOTAP–polymer hybrid nanoparticles can deliver mRNA molecules for the treatment of cancer32,33,34,35,36,37, infections38,39,40,41 and genetic disorders42. Incorporating carbonate apatite in DOTAP-based lipid nanoparticles increases the interaction between the particles and cellular membranes43. The delivery efficiency can further be improved by conjugating fibronectin to the lipid nanoparticles, which is a cellular adhesion protein accelerating the endocytic rate44.
Dimethyldioctadecylammonium bromide (DDAB), a quaternary ammonium lipid, can not only from complexes with mRNA but also stimulate innate immune responses45, thereby serving as immune adjuvant for mRNA vaccines46,47. DDAB and DOPE constitute the commercial product TransfectAce. The commercialized agent Lipofectamine is composed of DOPE and 2,3-dioleyloxy-N-[2-(sperminecarboxamido)ethyl]-N,N-dimethyl-1-propanaminium trifluoroacetate (DOSPA), a cationic lipid containing quaternary ammonium and spermine. Lipofectamine protocols have been optimized to deliver mRNA in diverse cell types, including alveolar cells, cardiac muscle cells and pluripotent stem cells48,49,50. 2-(((((3S,8S,9S,10R,13R,14S,17R)-10,13-dimethyl-17-((R)-6-methylheptan-2-yl)-2,3,4,7,8,9,10,11,12,13,14,15,16,17-tetradecahydro-1H-cyclopenta[a]phenanthren-3-yl)oxy)carbonyl)amino)-N,N-bis(2-hydroxyethyl)-N-methylethan-1-aminium bromide (BHEM-Cholesterol) was developed by modifying the head structure of 3β-[N-(N′,N′-dimethylaminoethane)-carbamoyl]cholesterol (DC-Cholesterol) with hydroxyl groups to improve fusion with cellular membranes51. Lipid nanoparticles containing BHEM-Cholesterol have been applied to deliver mRNA encoding clustered regularly interspaced short palindromic repeats (CRISPR)–CRISPR-associated protein 9 (CRISPR–Cas9) and tumour antigens52,53. Ethylphosphatidylcholine (ePC) was synthesized by introducing a third alkyloxy group into phosphatidylcholines to eliminate their negative charge. ePC-based lipid nanoparticles have been applied for mRNA-based cancer immunotherapies54,55 and protein replacement therapies56.
Ionizable lipids are protonated at low pH, which makes them positively charged, but they remain neutral at physiological pH (refs7,11,14). The pH-sensitivity of ionizable lipids is beneficial for mRNA delivery in vivo, because neutral lipids have less interactions with the anionic membranes of blood cells and, thus, improve the biocompatibility of lipid nanoparticles7,11,14. Trapped in endosomes, in which the pH is lower than in the extracellular environment, ionizable lipids are protonated and, therefore, become positively charged, which may promote membrane destabilization and facilitate endosomal escape of the nanoparticles7,11,14 Ionizable lipids originally developed for DNA transfection, such as (2S)-2,5-bis(3-aminopropylamino)-N-[2-(dioctadecylamino)acetyl]pentanamide (DOGS; Transfectam)57, N1-[2-((1S)-1-[(3-aminopropyl)amino]-4-[di(3-aminopropyl)amino]butylcarboxamido)ethyl]-3,4-di[oleyloxy]-benzamide (MVL5)58, DC-Cholesterol59 and N4-cholesteryl-spermine (GL67)60, have also been explored for mRNA delivery25,61,62,63.
The ionizable lipid 1,2-dilinoleyloxy-N,N-dimethyl-3-aminopropane (DLin-DMA) was initially synthesized for siRNA delivery64, and delivery efficacy was improved by modification of the linker and hydrophobic regions, resulting in 2,2-dilinoleyl-4-dimethylaminoethyl-[1,3]-dioxolane (DLin-KC2-DMA)65. Further optimization of the amine head group of DLin-KC2-DMA led to (6Z,9Z,28Z,31Z)-heptatriaconta-6,9,28,31-tetraen-19-yl 4-(dimethylamino) butanoate (DLin-MC3-DMA; MC3), which is a key delivery component of Onpattro, the first United States Food and Drug Administration (FDA)-approved siRNA drug18,66. MC3-based lipid nanoparticles have also been tested for mRNA therapeutics, such as protein replacement therapies56,67,68,69,70,71,72 and antiviral therapies73,74,75. Incorporation of biodegradable lipids improves the tolerability of lipid nanoparticles, by allowing fast metabolism while retaining mRNA delivery efficacy. The biodegradability of lipids can be increased by introducing ester motifs; for example, introducing ester bonds in the linker and lipidic tails of MC3 results in the lipid di((Z)-non-2-en-1-yl) 9-((4-(dimethylamino)butanoyl)oxy)heptadecanedioate (L319)76, which shows better delivery efficacy and faster elimination from the liver and plasma in vivo in comparison with MC3 (ref.76). Similarly, the biodegradable lipids heptadecan-9-yl 8-((2-hydroxyethyl)(8-(nonyloxy)-8-oxooctyl)amino)octanoate (Lipid 5)77, heptadecan-9-yl 8-((2-hydroxyethyl)(6-oxo-6-(undecyloxy)hexyl)amino) octanoate (Lipid H (SM-102))78 and ((4-hydroxybutyl)azanediyl)bis(hexane-6,1-diyl)bis(2-hexyldecanoate) (ALC-0315)79 have better in vivo delivery efficacy and pharmacokinetics than MC3. Of note, SM-102 and ALC-0315 are the ionizable delivery components in the mRNA-1273 and BNT162b COVID-19 vaccines, respectively17. Biodegradable lipids can also be made of both ester and disulfide motifs80,81,82,83,84,85. Cleavage of the disulfide bonds then drives an intraparticle nucleophilic attack on the ester linker, accelerating their degradation80,81,82,83,84,85.
A combinatorial library has been designed that contains lipid-like materials with different hydrophilic groups and multiple lipidic tails, highlighting the chemical diversity of ionizable lipids86. Many lipid-like materials, such as 1,1′-((2-(4-(2-((2-(bis(2-hydroxydodecyl)amino)ethyl) (2-hydroxydodecyl)amino)ethyl) piperazin-1-yl)ethyl)azanediyl) bis(dodecan-2-ol) (C12-200)87, tetrakis(8-methylnonyl) 3,3′,3″,3‴-(((methylazanediyl) bis(propane-3,1 diyl))bis (azanetriyl))tetrapropionate (306Oi10)88 and 3,6-bis(4-(bis(2-hydroxydodecyl)amino)butyl)piperazine-2,5-dione (cKK-E12)89, have been developed to deliver mRNA molecules in vivo90,91,92,93,94,95,96,97,98,99,100. For example, cKK-E12-based lipid nanoparticles are applied in cancer immunotherapies94,95 and genome editing96. Replacing the lipidic chains of cKK-E12 with alkenyl amino alcohols results in 3,6-bis(4-(bis((9Z,12Z)-2-hydroxyoctadeca-9,12-dien-1-yl)amino)butyl)piperazine-2,5-dione (OF-02), which improves mRNA delivery efficacy in vivo, compared with cKK-E12 (ref.101). Further altering the linkage of OF-02 leads to (((3,6-dioxopiperazine-2,5-diyl)bis(butane-4,1-diyl))bis(azanetriyl))tetrakis(ethane-2,1-diyl) (9Z,9′Z,9″Z,9‴Z,12Z,12′Z,12″Z,12‴Z)-tetrakis (octadeca-9,12-dienoate) (OF-Deg-Lin) and (((3,6-dioxopiperazine-2,5-diyl)bis(butane-4,1-diyl))bis(azanetriyl))tetrakis (butane-4,1-diyl) (9Z,9′Z,9″Z,9‴Z,12Z,12′Z,12″Z,12‴Z)-tetrakis (octadeca-9,12-dienoate) (OF-C4-Deg-Lin), which allow selective delivery of mRNA into the spleen102,103. The lipid-like material N1,N3,N5-tris(3-(didodecylamino)propyl)benzene-1,3,5-tricarboxamide (TT3) can deliver mRNA molecules encoding human factor IX104, CRISPR–Cas9 (ref.105), an interleukin-12 (IL-12) replicon106 and severe acute respiratory syndrome coronavirus 2 (SARS-CoV-2) antigens107. Hexa(octan-3-yl) 9,9′,9″,9‴,9″″,9‴″-((((benzene-1,3,5-tricarbonyl)ris(azanediyl)) tris (propane-3,1-diyl))tris(azanetriyl))hexanonanoate (FTT5), which is a biodegradable analogue of TT3, further improves the in vivo delivery efficacy of mRNA encoding human factor VIII and base editing components108. In addition, a series of aminoglycoside-derived lipids have been synthesized as mRNA delivery materials109,110,111,112.
Zwitterionic ionizable lipids can also be applied for mRNA delivery56,113,114,115,116; for example, lipids composed of a pH-switchable zwitterion and three hydrophobic tails assemble into a cone in the endosomal acidic environment, enabling membrane hexagonal transformation and allowing them to leave the endosome. Thus, lipid nanoparticle–mRNA formulations based on zwitterionic ionizable lipids can escape the endosome, leading to efficient protein expression and genome editing in vivo114. In addition to functioning as a delivery component, lipids can have therapeutic effects synergistic with mRNA-encoded proteins117,118,119. For example, lipids with a heterocyclic amine as head group can activate the stimulator of interferon genes (STING) signalling pathway in dendritic cells117. These lipids, as part of an mRNA vaccine, induce potent cytolytic T lymphocyte responses and inhibit tumour growth in mouse models117. Paclitaxel-conjugated lipids encapsulating tumour suppressor mRNA can be applied to integrate chemotherapy and gene therapy for triple-negative breast cancer118.
Other types of lipid
In addition to cationic or ionizable lipids, lipid nanoparticle–mRNA formulations typically contain other lipid components, such as phospholipids (for example, phosphatidylcholine and phosphatidylethanolamine), cholesterol or polyethylene glycol (PEG)-functionalized lipids (PEG-lipids)7,14,17. These lipids can improve nanoparticle properties, such as particle stability, delivery efficacy, tolerability and biodistribution7,14,17. For example, 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC), a phosphatidylcholine with saturated tails, has a melting temperature of ~54 °C and a cylindrical geometry that allows DSPC molecules to form a lamellar phase, which stabilizes the structure of lipid nanoparticles120. DSPC has been used in the mRNA-1273 and BNT162b2 COVID-19 vaccines17. DOPE is a phosphoethanolamine with two unsaturated tails, which has a melting temperature of ~30 °C and a conical shape120. DOPE tends to adopt an inverted hexagonal H(II) phase, which destabilizes endosomal membranes and facilitates endosomal escape of lipid nanoparticles90,120. Using DNA barcode-labelled oligonucleotides, the distribution of different lipid nanoparticle formulations can be analysed in a high-throughput manner in vivo121, for example, to quantify targeted delivery of nucleic acids in multiple tissues121. Based on this method, a series of phosphatidylcholines containing constrained adamantyl groups has been explored for mRNA delivery, including analysis of distribution in different cell types122.
Cholesterol can enhance particle stability by modulating membrane integrity and rigidity7,14,17. The molecular geometry of cholesterol derivatives can further affect delivery efficacy and biodistribution of lipid nanoparticles. For example, cholesterol analogues with C-24 alkyl phytosterols increase the in vivo delivery efficacy of lipid nanoparticle–mRNA formulations123. Here, the length of the hydrophobic tails of the cholesterol analogues, the flexibility of sterol rings and the polarity of hydroxy groups impact delivery efficacy123. In addition, lipid nanoparticles formulated with cholesterol derivatives adopt a polyhedral shape, and not a spherical shape, with multilamellarity and lipid partitioning124. Lipid nanoparticles containing cholesteryl oleate further show higher selectivity for liver endothelial cells than for hepatocytes125. Moreover, oxidative modifications on the cholesterol tail enable lipid nanoparticles to accumulate more in liver endothelial cells and Kupffer cells than in hepatocytes126.
PEG-lipids can have multiple effects on the properties of lipid nanoparticles14,17,72,127,128,129. The amount of PEG-lipids can affect particle size and zeta potential17,72. PEG-lipids can further contribute to particle stability by decreasing particle aggregation14,17,127, and certain PEG modifications prolong the blood circulation time of nanoparticles by reducing clearance mediated by the kidneys and the mononuclear phagocyte system (MPS)14,17,127,128,129. Finally, PEG-lipids can be used to conjugate specific ligands to the particle for targeted delivery. The extent of these effects depend on the proportions and properties of the PEG-lipids (such as PEG molar mass and lipid length)17,72,127,128,129. For example, 1,2-dimyristoyl-rac-glycero-3-methoxypolyethylene glycol-2000 (PEG2000-DMG) and 1,2-distearoyl-rac-glycero-3-methoxypolyethylene glycol-2000 (PEG2000-DSG) are neutral PEG-lipids, and the length of their saturated alkyl chains is C14 and C18, respectively129. Lipid nanoparticle–siRNA formulations containing PEG2000-DMG have shorter circulation times and higher delivery efficacy in vivo than formulations containing PEG2000-DSG129. This difference may be attributed to the faster dissociation of PEG2000-DMG from lipid nanoparticles, compared with PEG2000-DSG, which may benefit cellular uptake and endosomal escape of lipid nanoparticles128,129.
Overcoming physiological barriers
To function in vivo, lipid nanoparticle–mRNA formulations need to overcome multiple extracellular and intracellular barriers7,11 (Fig. 3a). First, mRNA needs to be protected from nuclease degradation in physiological fluids7,11. Second, the formulation should evade the interception by the MPS and clearance by renal glomerular filtration post systemic administration7,11. Third, lipid nanoparticle–mRNA systems need to reach target tissues, followed by internalization by target cells7,11. Finally, mRNA molecules must escape endosomes to reach the cytoplasm, where translation occurs7,11.
Lipid nanoparticle–mRNA formulations manufactured by rapid mixing exhibit a stable nanostructure17,130,131, in which mRNA molecules can be encapsulated in the interior core through electrostatic interactions with the lipids17,131. This structural feature protects mRNA molecules from nuclease degradation and increases nanoparticle stability in physiological fluids17,46. Incorporating PEG-lipids further decreases recognition by the MPS and clearance by renal filtration17,127. Additionally, targeted biodistribution of lipid nanoparticle–mRNA formulations can be improved by further modifying and optimizing the nanoparticle26,27,69,114,132,133,134,135; for example, nanoparticles can be coated with antibodies132 to deliver mRNA molecules into inflammatory leukocytes and epidermal growth factor receptor (EGFR)-positive tumour cells for treating inflammatory bowel disease69 and cancer133, respectively. Organ selectivity can also be achieved by adjusting the proportions of lipid components, for example, to design spleen-targeted mRNA vaccines26,27 or lung-targeted genome editing delivery systems114,134.
Once they reach target cells, lipid nanoparticles can be internalized by multiple mechanisms, including macropinocytosis and clathrin-mediated and caveolae-mediated endocytosis10,17. The endocytic pathway depends on the properties of the nanoparticle and the cell type100,108,136. Following cellular internalization, lipid nanoparticles are usually trapped in endosomal compartments137,138,139. Indeed, only a small amount of lipid nanoparticles may be able to escape from the endosome137,138,139. Thus, endosomal escape is crucial for effective mRNA delivery. Although the mechanism has not yet been fully understood, positively charged lipids may facilitate electrostatic interaction and fusion with negatively charged endosomal membranes, resulting in the leak of mRNA molecules into the cytoplasm7,11,14,17,100. Endosomal escape can be increased by optimizing the pKa values of ionizable lipids66,76,77,78,88,100,140. Furthermore, the properties of lipidic tails can affect endosomal escape of lipid nanoparticles64,97,114,141; for example, some lipids with branched tails show enhanced endosomal escape compared with their counterparts with linear tails, owing to stronger protonation at endosomal pH (ref.97). In addition, modulating the type (for example, DSPC and DOPE) and ratio of lipids may improve endosomal escape90,104,116,123,136,142.
Administration routes can greatly influence organ distribution, expression kinetics and therapeutic outcomes of lipid nanoparticle–mRNA formulations143,144. The administration route is often determined by the properties of the nanoparticles and therapeutic indications (Fig. 3b). After intravenous (i.v.) administration, many lipid nanoparticles can accumulate in the liver. The liver is inherently capable of producing secretory proteins and, therefore, i.v. administration of lipid nanoparticle–mRNA formulations can be used to produce proteins that are missing in inherited metabolic and haematological disorders, or to produce antibodies to neutralize pathogens or target cancer cells39,95,145,146,147. These applications require protein translation without stimulation of an immune response, which may limit the efficiency of repeated dosing. However, i.v. administration may also lead to accumulation of lipid nanoparticles in multiple lymph nodes throughout the body, which could increase immune responses to mRNA vaccines. For example, i.v. administration of mRNA vaccines has been shown to induce stronger antigen-specific cytotoxic T cell responses compared with local injection26,148,149. Broad distribution of mRNA vaccines in the body may lead to systemic adverse effects, and, thus, it may be necessary to develop lipid nanoparticles that allow targeted delivery of mRNA vaccines into tissues with abundant immune cells26,150.
Topical administration routes have also been explored for mRNA therapeutics. Topical administration aims at achieving local therapeutic effects; for example, local injection of lipid nanoparticle–mRNA formulations enables supplementation of therapeutic proteins in specific tissues, such as heart49,93, eyes56,72,151 and brain67,152. Of note, administration of mRNA encoding vascular endothelial growth factor (VEGF) has been shown to lead to functional protein expression in the skin even in the absence of lipid nanoparticles153. Indeed, mRNA delivery by direct injection into the heart muscle of patients undergoing coronary bypass surgery is currently being tested in a randomized phase II trial (NCT03370887)154. Moreover, lipid nanoparticle–mRNA formulations can be administered into the lungs by inhalation71, for example, MRT5005 (NCT03375047).
Local administration can also prime systemic responses; for example, intradermal (i.d.), intramuscular (i.m.) and subcutaneous (s.c.) injection are commonly used for vaccination17,155, because resident and recruited antigen-presenting cells (APCs) are present in the skin and muscle, which can internalize and process mRNA-encoded antigens17,155. Furthermore, the vascular and lymphatic vessels of these tissues help APCs and mRNA vaccines to centre the draining lymph nodes to stimulate T cell immunity17,155. Indeed, both i.m. and i.d. administration of lipid nanoparticle–mRNA vaccines produce robust immune responses at a well-tolerated dose in human trials156,157. Vaccination can also be done by intranasal administration, because APCs in the peripheral lymph nodes can readily endocytose administered lipid nanoparticle–mRNA formulations17,34,155,158,159,160. In addition, lipid nanoparticle–mRNA formulations encoding immune stimulators can be directly delivered into tumour tissue by intratumoural injection106,161,162,163, to boost a local pro-inflammatory environment, which leads to immune cell activation and subsequent priming of systemic anticancer responses106,161,162,163. Finally, in utero administration of lipid nanoparticle–mRNA formulations can be applied to deliver mRNA to mouse fetuses164, achieving protein expression in fetal livers, lungs and intestines164.
Considerations for clinical translation
The properties of lipid nanoparticle–mRNA formulations need to be carefully characterized and considered for the desired application. Lipid nanoparticle–mRNA formulations may need different properties as vaccines than as therapeutics to achieve optimal therapeutic effects, for example, distinct biodistribution profiles. Vaccines need to interact with immune cells, whereas therapeutics are targeted to specific organs. Therefore, lipid nanoparticle–mRNA formulations should be designed according to biomedical demand. To translate lipid nanoparticle–mRNA systems from bench to bedside, good manufacturing practice (GMP) is crucial to ensure drug quality and therapeutic effects, in addition to considerations such as storage conditions and safety profiles.
Good manufacturing practice
The preparation of a linearized DNA template is the initial step of GMP production of mRNA2,4,165,166. Based on the DNA template, the mRNA is then transcribed in vitro in the presence of an RNA polymerase and ribonucleoside triphosphates2,4,165,166. The residual DNA template is removed by DNase digestion and the mRNA molecules are capped by chemical or enzymatic methods2,4,165,166. Finally, mRNA is purified by microbeads-based precipitation or chromatographic methods to remove the enzymes, free nucleotides, truncated nucleic acid fragments and double-stranded RNA2,4,165,166. The purified mRNA can be dissolved in a storage buffer, filtered for sterilization and frozen for long-term storage2,4,165,166. To increase the stability and translational efficiency of mRNA, various approaches have been explored to optimize its structural elements (Box 1).
Historically, lipid nanoparticle–nucleic acid formulations were produced by thin-film hydration, reverse-phase evaporation and other methods167. The sizes of lipid nanoparticles were further homogenized by extrusion techniques167. Lipid nanoparticle–mRNA formulations are now commonly manufactured by rapid mixing; here, an ethanol phase (lipid components) and an aqueous phase (mRNA molecules) are mixed under specific conditions (that is, pH and flow rate)17,131. This technique allows reproducible and scalable production of lipid nanoparticle–mRNA formulations that show high encapsulation efficiency and homogeneous size distribution17,131. mRNA is susceptible to degradation and, thus, formulation buffers should be free of any ribonuclease contaminations2,4. Lipid nanoparticle–mRNA formulations are further purified to remove organic solvents and residual components, and the final mRNA concentration can be further increased by enrichment. The filtered and frozen lipid nanoparticle–mRNA formulations are then subject to a series of GMP standard tests, including evaluation of physical parameters (such as mRNA encapsulation, particle sizes, charges), compendial testing (such as sterility, bacterial endotoxins, particulate matter, osmolality) and other quality testing.
Stability and storage
Storage conditions of lipid nanoparticle–mRNA formulations are an important consideration for their clinical translation, because storage (aqueous, freezing and lyophilized storage) and the type of cryoprotectants (sucrose, trehalose or mannitol) affect the long-term stability of lipid nanoparticle–mRNA formulations168. For example, the addition of 5% (w/v) sucrose or trehalose to lipid nanoparticle–mRNA formulations, stored in liquid nitrogen, allows maintenance of mRNA delivery efficacy for at least 3 months in vivo168. Of note, the authorized COVID-19 mRNA vaccines are both stored in freezing conditions in the presence of sucrose17. mRNA-1273 is stored at −15 °C to −20 °C and is directly injected after thawing17, whereas BNT162b2 is stored at −60 °C to −80 °C and requires thawing and dilution by saline before injection17. Recently, the European Medicines Agency (EMA) has approved storage of BNT162b2 at −15 °C to −25 °C for 2 weeks based on new stability data. Although cold-chain transportation can maintain vaccine activity, the development of lipid nanoparticle–mRNA formulations that do not require cold or frozen storage would not only decrease production and transportation costs but also expedite the process of vaccination. Therefore, it is important to investigate the factors impacting long-term storage of lipid nanoparticle–mRNA formulations.
The safety profile of lipid nanoparticle–mRNA formulations correlates with the lipid components and mRNA molecules. Lipid components may activate host immune responses following systemic or local administration; for example, PEG-lipids could induce hypersensitivity reactions by stimulating the complement system127,169. Moreover, anti-PEG antibodies could result in fast systemic clearance of subsequently administered PEGylated nanoparticles by accelerated blood clearance127,169. The accelerated blood clearance phenomenon may change the bioavailability and biodistribution of the drug encapsulated in PEGylated nanoparticles and, thus, cause side effects127,169. To ameliorate safety concerns, numerous natural and synthetic polymers have been investigated as alternatives to PEG, of which several are under evaluation in clinical trials127,169. Cationic and ionizable lipids have also been reported to stimulate the secretion of pro-inflammatory cytokines and reactive oxygen species170,171,172,173. Although the immunogenicity of these lipids has not yet been fully understood, complement system and Toll-like receptors may participate in innate immune activation170,173,174,175. Cytotoxicity of lipid materials is also a safety concern, depending on the dose, lipid properties and cell types176,177. In vivo application of lipid nanoparticles has been reported to induce liver and lung injuries in rodents170,173, which may be attributed to the cytotoxicity of the materials and the induction of pro-inflammatory factors171,178. To improve the biocompatibility of lipid nanoparticles, biodegradable lipids can be applied76,77,78,108,179.
The immunogenicity of IVT mRNA is another safety concern, although eliciting cellular and humoral immunity may be advantageous for vaccination. Nevertheless, immune responses to IVT mRNA may also suppress antigen expression and negatively affect vaccine efficacy175,180,181. Moreover, immune activation is undesirable for some mRNA applications, such as protein replacement therapies and genome editing. To minimize the immunogenicity of mRNA, two approaches are commonly used. Chemical modifications of specific IVT mRNA nucleotides, such as pseudouridine (ψ) and N1-methylpseudouridine (m1ψ), can reduce innate immune sensing of exogenous mRNA translation2,4,7,182. Chromatographic purification can remove double-stranded RNA, an analogue of viral genome, in IVT mRNA preparations, diminishing immune activation and increasing translational efficiency2,4,7,183. The IVT mRNA molecules used in the mRNA-1273 and BNT162b2 COVID-19 vaccines were prepared by replacing uridine with m1ψ17,19,21, and their sequences were optimized to encode a stabilized pre-fusion spike protein with two pivotal proline substitutions17,19,21.
Preclinical studies and clinical trials
The features of lipid nanoparticle–mRNA formulations have been thoroughly preclinically and clinically investigated, which has allowed the rapid development and clinical use of the COVID-19 lipid nanoparticle–mRNA vaccines. For example, the clinical-grade COVID-19 vaccine, mRNA-1273, was produced within a month after the SARS-CoV-2 genome sequence was available15,17. About 2, 5 and 6 months from sequence availability, clinical trial phases I, II and III were initiated, respectively15,17. Finally, mRNA-1273 obtained Emergency Use Authorization from the FDA and conditional marketing authorization from the EMA within a year15,17. Many other lipid nanoparticle–mRNA formulations are in clinical trials for the treatment of infectious diseases, cancer and genetic disorders2,4,8,12,13,14 (Tables 1,2). Moreover, mRNA-based cellular reprogramming, tissue regeneration and genome editing have shown therapeutic potential in preclinical studies2,4,8,12,13,14.
Vaccines are the most effective approach to control and eradicate epidemics. The first mRNA vaccine was made of liposomes and mRNA encoding an influenza virus nucleoprotein184. This vaccine, designed in 1993, was able to induce virus-specific cytotoxic T cell responses in mice184. Since then, lipid nanoparticle–mRNA formulations have emerged as a potent alternative to conventional vaccine platforms, owing to their unique features4,15,17. First, mRNA is a non-infective and non-integrating agent with the ability to encode a broad range of antigens4,15,17. Second, mRNA vaccines can combine different antigen mRNAs; for example, six separate mRNAs have been incorporated in a cytomegalovirus vaccine, five of which encode a single pentameric antigen and one encodes a glycoprotein antigen185. Finally, GMP-grade lipid nanoparticle-mRNA vaccines can be manufactured for specific antigens in a short period of time, compared with other vaccine platforms, such as recombinant proteins and inactivated vaccines2,4,15,17. These features make lipid nanoparticle–mRNA formulations a flexible and on-demand vaccine platform to rapidly respond to emerging infectious pathogens4,15,17. However, the instability and short half-life of mRNA need to be carefully considered. In addition, safety concerns and storage conditions of lipid nanoparticles need to be determined before clinical use.
To address these concerns, the engineering of mRNA molecules (Box 1) and the design of lipid nanoparticles have been optimized2,4,7,8,9,10,11,12,13,14,15,16,17, which has contributed to the rapid development and clinical assessment15,17 of the two COVID-19 mRNA vaccines, mRNA-1273 (NCT04470427)19,20 and BNT162b2 (NCT04368728)21. Both vaccines use ionizable lipid nanoparticles to deliver nucleoside-modified mRNA encoding the full-length spike protein of SARS-CoV-2 (Fig. 4). Applying a prime–boost vaccination method, the vaccines induce high levels of antigen-specific antibodies and elicit robust T helper 1 cell responses19,20,21. Moreover, the vaccines showed similar efficacy (~95%) in phase III clinical trials19,20,21. Other COVID-19 vaccines based on lipid nanoparticle–mRNA formulations are also under evaluation in different clinical phases (Table 1). In preclinical studies, some vaccine candidates showed protective effects by delivering self-amplifying RNA encoding the spike protein40,186,187 (Box 2), a cocktail of mRNAs encoding three viral proteins74, modified mRNA encoding the receptor-binding domain188 or spike mRNA with engineered untranslated regions107.
Lipid nanoparticle–mRNA vaccines are also being investigated as influenza vaccines29,41,156,157,159,184,189,190,191, with some formulations in clinical trials (Table 1). Haemagglutinin is an essential surface antigen of influenza viruses156,157. The mRNA-1440 and mRNA-1851 vaccines, which are composed of lipid nanoparticles and mRNA encoding haemagglutinin from H10N8 and H7N9 influenza viruses, respectively, have completed phase I clinical studies (NCT03076385 and NCT03345043)156,157. After i.m. prime–boost vaccination, humoral immune responses were evaluated by haemagglutination inhibition (HAI) and microneutralization (MN) assays. A 100-μg dose level induced 78.3% (HAI) and 87.0% (MN) seroconversion for H10N8 (refs156,157) and a 50-μg dose level resulted in 96.3% (HAI) and 100% (MN) seroconversion for H7N9 (refs156,157). Lipid nanoparticle–mRNA formulations are further being explored for Zika virus vaccines38,190,192,193,194. The vaccine mRNA-1893 is a clinical candidate that contains lipid nanoparticles with mRNA encoding Zika virus premembrane and envelope (prM-E) proteins193,194. According to mRNA-1893 interim phase I data (NCT04064905) reported by Moderna, 10-µg and 30-µg dose levels (prime–boost regimen) induced 94% and 100% seroconversion, respectively, and both dose levels were generally well tolerated.
A series of clinical trials of mRNA vaccines have been initiated against human metapneumovirus, cytomegalovirus, respiratory syncytial virus, rabies virus and chikungunya virus (Table 1). Furthermore, lipid nanoparticle–mRNA vaccines have been tested against other viruses in animal models, including human immunodeficiency virus28,144,181,190, Powassan virus195, Venezuelan equine encephalitis virus196, dengue virus73 and Ebola virus197.
Apart from viral infections, lipid nanoparticle–mRNA vaccines have been reported to induce immune protection against parasitical31 and bacterial30,198 infections. In addition, lipid nanoparticle–mRNA formulations have been applied to produce therapeutic proteins or antibodies39,75,145,146, to edit virus genomes105 and to engineer immune cells136. For example, a vitamin C-derived lipid nanoparticle allows mRNA delivery into primary macrophages136. Adoptive transfer of macrophages engineered by delivering mRNA that encodes an antimicrobial peptide considerably reduced bacterial burden and increased survival in mice with multidrug-resistant bacterial sepsis136. Furthermore, the lipid nanoparticle–mRNA formulation mRNA-1944 (NCT03829384), designed to generate anti-chikungunya virus antibody (CHKV-IgG) in vivo, is under clinical evaluation. A single i.v. injection of 0.1, 0.3 and 0.6 mg kg−1 lipid nanoparticle–mRNA formulation produced 2.0, 7.9 and 10.2 µg ml−1 CHKV-IgG 24 h post injection, respectively. The half-life of CHKV-IgG was about 69 days and the dose levels were reasonably well tolerated, including 0.3 mg kg−1 given twice a week apart.
The attempt of mRNA-based cancer immunotherapies dates back to 1995, when i.m. injection of mRNA encoding carcinoembryonic antigens was shown to induce antigen-specific immune responses in mice199. Various cancer vaccines based on lipid nanoparticle–mRNA formulations are currently in clinical trials (Table 1). For example, FixVac, which was developed based on the RNA-LPX formulation, is a systemic mRNA vaccine encoding four non-mutated antigens of melanoma200. The interim analysis from the phase I trial (NCT02410733) showed that the metabolic activity of the spleen increased post the sixth immunization, indicating targeted delivery of FixVac and activation of resident immune cells200. After the eighth immunization, more than 75% of patients generated immune responses against at least one tumour-associated antigen, and CD8+ T cells played a major role in high-magnitude T cell responses200. Moreover, a combination of FixVac/anti-programmed cell death protein 1 (PD1) antibody augmented the antitumour effect of FixVac, resulting in a >35% tumour regression rate in immune checkpoint inhibitor-experienced patients200. To further improve vaccine efficacy, APC uptake and T cell activation can be optimized; for example, mannose-modified lipid nanoparticle–mRNA formulations are preferentially taken up by dendritic cells150,201,202. The efficacy of cancer vaccines can also be boosted by co-delivery of antigen mRNA with adjuvants32,63,94,203,204,205,206, co-stimulatory molecules148,150,207,208 and immune checkpoint inhibitors200,201,202,209,210,211.
Neoantigens, generated by somatic mutations in cancer cells, are usually tumour-specific and have high immunogenicity4,11. Neoantigens are often different between individual patients, allowing the development of personalized vaccines4,11. For example, intranodal vaccination with free mRNA encoding ten neoepitopes of 13 patients with metastatic melanoma generated T cell immunity against multiple neoepitopes in all patients209. Several personalized cancer vaccines using lipid nanoparticle–mRNA formulations have also entered clinical trials210,211,212. For example, mRNA-4157 is a personalized cancer vaccine encoding up to 34 neoantigens210,211. A phase I study (NCT03897881) has been performed to evaluate the immunogenicity of mRNA-4157 alone and in combination with immune checkpoint inhibitors in patients with resected and unresectable solid tumours, respectively210,211. In the monotherapy group, 14 out of 16 patients remained disease-free during the study, with a median follow-up time of 8 months210,211. In the combination group, the overall response rate in the cohort (human papillomavirus-negative, immune checkpoint inhibitor-naive, head and neck squamous cell carcinomas) was 50% and the median progression-free survival was 9.8 months210,211. Using a similar lipid nanoparticle formulation, mRNA vaccination has also been shown to elicit specific T cell responses in patients with gastrointestinal cancer (NCT03480152)212.
mRNA vaccines can further be applied to overcome insufficient stimulation of chimeric antigen receptor (CAR) T cells in the therapy of solid tumours213. For example, the RNA-LPX formulation can be used to deliver mRNA encoding claudin 6 (CLDN6), a target for CAR T cell therapy in solid tumours213. i.v. injection of this vaccine resulted in CLDN6 expression on splenic dendritic cells and macrophages213, promoting the activation of adoptively transferred CLDN6-CAR T cells and leading to suppression of large tumours in mice at a sub-therapeutic CAR T cell dose213.
Alternatively to vaccination, a pro-inflammatory tumour microenvironment can be induced by lipid nanoparticle–mRNA formulations delivering cytokines or co-stimulatory molecules33,106,161,163,214 (Table 2). For example, mRNA-2416, a lipid nanoparticle encapsulating mRNA encoding human OX40L (a ligand of OX40), is in clinical evaluation for the treatment of patients with solid tumours (NCT03323398)214. In this trial, mRNA-2416 was intratumourally administered every 2 weeks for up to 12 doses, with four dose levels from 1 to 8 mg (ref.214). mRNA-2416 was generally well tolerated at different does levels214. Moreover, the injected lesions showed an increase in OX40L expression and enhanced T cell activation214. Encouraged by these results, mRNA-2752, a lipid nanoparticle formulated with mRNA encoding human OX40L, IL-23 and IL-36γ, entered clinical evaluation (NCT03739931)163,215,216. mRNA-2752 was designed to induce a pro-inflammatory tumour microenvironment and to simultaneously strengthen T cell expansion, as well as memory responses215,216. mRNA-2752 was intratumourally administered every 2 weeks for up to seven doses, alone or in combination with infusion of durvalumab215,216. In the 22 patients (monotherapy: n = 15; combination: n = 7), six had stable disease, one had partial responses with 52% tumour reduction and five showed tumour shrinkage in treated and/or untreated sites215,216. Lipid nanoparticle–mRNA formulations have also been investigated for ex vivo engineering of CAR T cells217 and for the production of antibodies, such as anti-CD20 (ref.146), anti-human epidermal growth factor receptor 2 (HER2)95 and anti-CD3/claudin 6 (ref.147). Cancers are often accompanied by mutations in the genome and, therefore, correction of these mutations could be an effective approach for cancer therapies. For example, restoration of the tumour suppressor gene TP53 can induce tumour cell apoptosis and sensitize tumour cells to chemotherapeutics in vivo118,218. Similarly, the regulation of other tumour-associated genes, such as PLK1 (ref.133), Bax219, Maspin37, PUMA70 and PTEN220, can delay tumour growth in vivo.
Genetic disorders are caused by inherited or acquired gene mutations, which can cause abnormal protein expression12. The supplement of therapeutic proteins can relieve clinical symptoms but can often not provide lasting treatments or cures. Alternatively, gene therapy seeks to modify malfunctioning genetic expression. mRNA-based protein replacement therapies have also emerged as a promising alternative to protein drugs, because mRNA can be translated into desired proteins with in situ post-translational modifications in host cells12. Moreover, mRNA can restore different types of protein, including secretory proteins, intracellular proteins and transmembrane proteins12.
Clinical trials of protein replacement therapies using lipid nanoparticle–mRNA formulations have mainly focused on inherited metabolic disorders thus far, including ornithine transcarbamylase deficiency (NCT03767270), methylmalonic acidaemia (NCT03810690) and propionic acidaemia (NCT04159103) (Table 2). These diseases are characterized by genetic deficiency of key enzymes, leading to an inability to process certain metabolic products12. The excessive accumulation of metabolites then results in clinical symptoms and may lead to death12. Therefore, the supplement of desired enzymes by lipid nanoparticle–mRNA formulations can slow down disease progression42,221. The therapeutic potential of mRNA-based protein replacement therapies has also been tested in other metabolic disorders in preclinical studies, including hereditary tyrosinaemia type I (HTI)142, acute intermittent porphyria222,223, Fabry disease224,225, Crigler–Najjar syndrome type 1 (ref.226), α1 antitrypsin deficiency227, methylmalonic acidaemia/aciduria228, arginase deficiency229, citrin deficiency230 and glycogen storage disease type I (ref.231). In addition, mRNA-based protein replacement therapies have been applied to haematological diseases (for example, haemophilia A232, haemophilia B91,104,233 and thrombotic thrombocytopaenic purpura234), central nervous system disorders67,152 (for example, Friedreich’s ataxia67), skin diseases235,236 (for example, elastin deficiency235) and hearing loss237 in preclinical studies.
Gene-editing tools further provide the opportunity to correct mutated genes in genetic disorders. Gene-editing components can be delivered by lipid nanoparticle–mRNA formulations to treat genetic diseases, including HTI92,238, hypercholesterolaemia81,96,105,239, lipoprotein metabolism disorders85 and transthyretin amyloidosis239,240, which has been demonstrated in preclinical studies. Intellia Therapeutics further initiated a phase I clinical trial (NCT04601051) to study the safety, pharmacokinetics and pharmacodynamics of NTLA-2001 (lipid nanoparticles encapsulating gene-editing components) in patients with hereditary transthyretin amyloidosis.
mRNA-based protein replacement therapies are also in clinical trials for the treatment of cystic fibrosis. Patients with cystic fibrosis usually suffer from repeated airway infections and chronic respiratory problems because of the defective cystic fibrosis transmembrane conductance regulator (CFTR), a chloride channel on epithelial cells12. Lipid nanoparticles encapsulating CFTR mRNA can restore chloride secretion in Cftr-knockout mice68. Translate Bio has started a clinical trial (NCT03375047) to evaluate the safety and tolerability of nebulized lipid nanoparticle–mRNA formulations (MRT5005) in patients with cystic fibrosis. In this phase I/II study, patients received a single dose of MRT5005 at three dose levels (8, 16 and 24 mg). MRT5005 was well tolerated at the 8-mg and 16-mg dose levels, and no serious side events were observed at any dose level. The lung function was evaluated by percent predicted forced expiratory volume in 1 s (PPFEV1). According to the interim report, the three patients who received the 16-mg dose showed maximal PPFEV1 increases of 11.1%, 13.6% and 22.2%, respectively, on day 8 post nebulizing. mRNA-based protein replacement therapies are also being explored for heart241, liver242, lung243 and other organ diseases12.
Conclusions and future directions
Progress in mRNA technologies and lipid nanoparticle-based delivery systems has allowed the development of mRNA COVID-19 vaccines at unprecedented speed, demonstrating the clinical potential of lipid nanoparticle–mRNA formulations and providing a powerful tool against the SARS-CoV-2 pandemic. A variety of lipid nanoparticles have been explored and optimized for mRNA delivery, providing valuable information for the future design of mRNA therapeutics. Based on the lessons and experiences from clinical studies, lipid nanoparticle–mRNA formulations can be further improved.
The in vivo translation efficiency of mRNA molecules could be further increased by RNA engineering. To achieve effective translation, mRNA requires five structural elements, including the 5′ cap, 3′ poly(A) tail, protein-coding sequence and 5′ and 3′ untranslated regions (UTRs)2,4. The sequences of these elements regulate translation initiation, translation termination and post-transcriptional modification of mRNA molecules2,4. Thus, sequence engineering of these elements could improve translation in vivo. For example, optimization of the UTRs or the coding sequences results in increased protein expression, compared with wild-type controls107,244. In addition, circular RNA (circRNA) can be synthesized to optimize mRNA properties245,246 (Box 2). circRNA lacks the free ends necessary for nuclease-mediated degradation and, therefore, has a longer half-life than its linear mRNA counterpart245,246.
Moreover, the delivery efficacy of mRNA could be improved, for example, by rational design of lipids through modulation of head groups and hydrophobic tails to increase cellular uptake and endosomal escape of lipid nanoparticle–mRNA formulations64,66,76,77,78,88,97,100,114,140,141. Furthermore, hybrid nanoparticles may integrate the advantages of individual components to improve mRNA delivery potency. For example, pH-responsive polymers, such as poly (β-amino ester), can be incorporated into lipid nanoparticles to facilitate endosomal escape of mRNA molecules160. Polymers, such as polyethyleneimine, protamine and polyaspartamide derivatives, are already widely used for mRNA delivery7,8,9,10,11,12,13,14,15,16,17. In addition, charge-altering releasable transporters162,247 and modified dendrimers248 can effectively deliver mRNA molecules in vitro and in vivo. Naturally derived membrane lipids (for example, exosomes and cell membranes) can also be applied for mRNA delivery116,249,250.
Organ-specific and cell-specific delivery of lipid nanoparticles can be achieved by modulating the lipid structures. For example, alteration of the alkyl length of a lipid results in selective accumulation of lipid nanoparticle–mRNA formulations in the liver or spleen114. Alternatively, biomimetic lipids can be designed to achieve organ-targeted delivery. For example, neurotransmitters are endogenous chemicals that can cross the blood–brain barrier and participate in neurotransmission82. Thus, neurotransmitter-derived lipids can be used for mRNA delivery to the brain following i.v. injection82. Testing and comparing the cell distribution of many different lipid nanoparticle formulations remains challenging. However, barcoded nanoparticles allow in vivo high-throughput profiling of lipid nanoparticle distribution at the cell level121. For example, barcoding has been applied to study how the structure of cholesterol derivatives impact cell selectivity of lipid nanoparticles, revealing that selective accumulation in liver endothelial cells, Kupffer cells and hepatocytes125,126 depends on cholesterol structures. Such large data sets will pave the way for a more profound understanding of the relationship between lipid nanoparticle properties and biodistribution.
Finally, biodegradability and multifunctionality should be considered for the design of lipid nanoparticles. Biodegradable lipids enable fast elimination of lipid nanoparticles from plasma and tissues, improving their safety and tolerability. Notably, biodegradable lipids are part of the mRNA-1273 and BNT162b2 COVID-19 mRNA vaccines. In addition to serving as delivery component, lipids may have therapeutic effects synergistic with mRNA-encoded proteins. Such multifunctional lipid materials include self-adjuvant lipids, which boost vaccine efficacy117,119, and paclitaxel-derived lipids, which allow integration of chemotherapies and gene therapies for the treatment of cancer118.
In summary, mRNA has shown great therapeutic potential in a number of clinical trials and in clinical applications. The development of next-generation lipid nanoparticles and other types of delivery material will further enable mRNA-based therapies for a broad range of diseases and improve health care in the near future.
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This work was supported by the Maximizing Investigators’ Research Award R35GM119679 from the National Institute of General Medical Sciences (to Y.D.) and grant EB000244 from the National Institute of Biomedical Imaging and Bioengineering (to R.L.). We acknowledge Y. Zhang for his help with chemical structures. All authors reviewed and edited the manuscript before submission.
Y.D. is a scientific advisory board member of Oncorus, Inc. and serves as a consultant of Rubius Therapeutics. T.Z. is an employee of Moderna, Inc. R.L. is a founding scientific advisory board member of Alnylam and a founder and board member of Moderna, Inc. A list of entities with which R.L. is involved, compensated or uncompensated is provided in the supplementary information. X.H. declares no competing interests.
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GMP standard tests: https://www.accessdata.fda.gov/drugsatfda_docs/nda/2018/210922Orig1s000ChemR.pdf
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Hou, X., Zaks, T., Langer, R. et al. Lipid nanoparticles for mRNA delivery. Nat Rev Mater 6, 1078–1094 (2021). https://doi.org/10.1038/s41578-021-00358-0
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