US20190307689A1

US20190307689A1 - Lipid nanoparticles for transfection and related methods

Info

Publication number: US20190307689A1
Application number: US16/449,176
Authority: US
Inventors: Euan Ramsay; R. James Taylor; Colin Walsh; Nathan M. Belliveau; Pieter R. Cullis; Timothy Leaver; Andre Wild
Original assignee: University of British Columbia
Current assignee: University of British Columbia
Priority date: 2013-03-15
Filing date: 2019-06-21
Publication date: 2019-10-10
Also published as: CN105143456A; CA2906732C; CA2906732A1; WO2014172045A8; EP2971013A4; EP2971013A1; JP6605446B2; WO2014172045A1; JP2016515815A; EP2971013B1; US10342760B2; US20160022580A1

Abstract

Transfection reagent composition, lipid nanoparticles prepared from the transfection reagent composition, kits that include the transfection reagent composition, and methods for making and using lipid nanoparticles prepared from the transfection reagent composition. Lipids when dispersed in aqueous media readily form liposomes, such as unilamellar vesicles and multilamellar vesicles. Liposomes have been used successfully to encapsulate and deliver a wide range of chemicals including nucleic acids, proteins and, small molecule drugs, to cells.

Description

CROSS-REFERENCE TO RELATED APPLICATION

This application is a divisional of U.S. patent application Ser. No. 14/775,539, filed Sep. 11, 2015, which is a National Stage of International Patent Application No. PCT/US2014/029116, which claims the benefit of U.S. Patent Application No. 61/798,495, filed Mar. 15, 2013, expressly incorporated herein by reference in its entirety.

STATEMENT REGARDING SEQUENCE LISTING

The sequence listing associated with this application is provided in text format in lieu of a paper copy and is hereby incorporated by reference into the specification. The name of the text file containing the sequence listing is 43935_Sequence_Final_2014-03-14.txt. The text file is 748 bytes; was created on Mar. 14, 2014; and is being submitted via EFS-Web with the filing of the specification.

BACKGROUND OF THE INVENTION

Lipids when dispersed in aqueous media readily form liposomes, such as unilamellar vesicles and multilamellar vesicles. Liposomes have been used successfully to encapsulate and deliver a wide range of chemicals including nucleic acids, proteins and small molecule drugs, to cells.
Cationic liposomes prepared from a composition of cationic lipids and phospholipids, readily form aggregates with anionic macromolecules such as DNA and RNA. These cationic liposome—nucleic acid aggregates are often engineered such that the net charge of the complex is positive, which is believed to facilitate interaction with the anionic cell surface thereby enhancing uptake of the encapsulated cargo and subsequent cell transfection. An example of a cationic lipid composition that is commonly used for the transfection of cells in vitro is N-[1-(2,3-dioleoyloxy)propyl]-N,N,N-trimethylammonium chloride (DOTMA) combined with dioleoylphosphatidylethanolamine (DOPE) at a molar ratio of 1:1.
The size and structure of cationic liposome—nucleic acid aggregate is dependent on the lipid composition and the method of manufacture. These structures can range in size from several hundred nanometers to micrometers and often have heterogeneous morphologies when visualized by electron microscopy, including the classic “spaghetti and meatballs” conformation.
Cationic liposome—nucleic acid aggregates have limited effectiveness in primary cells, i.e., cells harvested from a living organism. This is believed to be the result of toxicity due to excessive cationic charge. Toxicity plus large particle size also limits use of cationic liposome—nucleic acid aggregates for transfection in vivo.
Lipid nanoparticles (LNP) are the most clinically advanced drug delivery systems, with seven LNP-based drugs having received regulatory approval. These approved drugs contain small molecules such as anticancer drugs and exhibit improved efficacy and/or reduced toxicity compared to the “free” drug. LNP carrier technology has also been applied to delivery of “genetic” anionic macromolecules such as plasmids for protein expression or small interfering RNA (siRNA) oligonucleotides (OGN) for gene silencing.
Recent advances in LNP technology and the cationic lipids used to encapsulate and deliver of genetic drugs, have enabled siRNA-LNP that have been shown to overcome the inherent liabilities of cationic liposome—nucleic acid aggregates and mediate silencing of therapeutically relevant target genes in difficult-to-transfect primary cells and animal models, including non-human primates following intravenous (i.v.) injection. These siRNA-LNP are currently under evaluation in several clinical trials.
A variety of methods have been developed to formulate LNP systems containing genetic drugs. These methods include mixing preformed LNP with OGN in the presence of ethanol, or mixing lipid dissolved in ethanol with an aqueous media containing OGN, and result in LNP with diameters of 100 nm or less and OGN encapsulation efficiencies of 65-95%. Both of these methods rely on the presence of cationic lipid to achieve encapsulation of OGN and poly(ethylene glycol) (PEG) lipids to inhibit aggregation and the formation of large structures. The properties of the LNP systems produced, including size and OGN encapsulation efficiency, are sensitive to a variety of formulation parameters such as ionic strength, lipid and ethanol concentration, pH, OGN concentration and mixing rates. In general, parameters such as the relative lipid and OGN concentrations at the time of mixing, as well as the mixing rates are difficult to control using current formulation procedures, resulting in variability in the characteristics of LNP produced, both within and between preparations.
Microfluidic devices rapidly mix fluids at the nanoliter scale with precise control over temperature, residence times, and solute concentrations. Controlled and rapid microfluidic mixing has been previously applied in the synthesis of inorganic nanoparticles and microparticles, and can outperform macroscale systems in large-scale production of nanoparticles. Microfluidic two-phase droplet techniques have been applied to produce monodisperse polymeric microparticles for drug delivery or to produce large vesicles for the encapsulation of cells, proteins, or other biomolecules. The use of hydrodynamic flow focusing, a common microfluidic technique to provide rapid mixing of reagents, to create monodisperse liposomes of controlled size has been demonstrated. This technique has also proven useful in the production of polymeric nanoparticles where smaller, more monodisperse particles were obtained, with higher encapsulation of small molecules as compared to bulk production methods.
Despite the numerous products available for cell transfection, a need exists for devices and methods for the efficient delivery of siRNA OGN and other anionic macromolecules to difficult-to-transfect primary cells in vitro and to target cells in vivo. The present invention seeks to fulfill this need and provides further related advantages to address a major problem impeding the validation of aberrant genes, identified through genome sequencing of disease cells, as potential drug or biomarker targets.

SUMMARY OF THE INVENTION

In one aspect, the invention provides a transfection reagent composition comprising lipids and surfactants.
In one embodiment, the transfection reagent comprises (a) one or more cationic lipids, (b) one or more second lipids, and (c) one or more sterols, and (d) one or more surfactants.
In one embodiment, the cationic lipid is 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate. In certain embodiments, the particle comprises from about 30 to about 95 mole percent cationic lipid.
In one embodiment, the second lipid is 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC).
In one embodiment, the sterol is cholesterol.
In one embodiment, the surfactant is polyoxyethylene (20) oleyl ether. In a further embodiment, the surfactant is polyoxyethylene (40) stearate. In certain embodiments, the particle comprises from about 0.1 to about 20 mole percent surfactant.
In another embodiment, the lipid nanoparticle comprises (a) one or more cationic lipids, (b) one or more second lipids, (c) one or more sterols, and (d) one or more surfactants; as defined herein. In one embodiment, the cationic lipid is 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate. In one embodiment, the second lipid is 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC). In one embodiment, the sterol lipid is cholesterol. In one embodiment, the surfactant is polyoxyethylene (20) oleyl ether.
In another embodiment, the lipid nanoparticle comprises (a) one or more cationic lipids, (b) one or more second lipids, (c) one or more sterols, and (d) one or more surfactants; as defined herein. In one embodiment, the cationic lipid is 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate. In one embodiment, the second lipid is 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC). In one embodiment, the sterol lipid is cholesterol. In one embodiment, the surfactant is Polyoxyethylene (40) stearate.
In other aspects, the invention provides a lipid nanoparticle comprising a transfection reagent composition and an anionic macromolecule, wherein the lipid nanoparticle comprises a substantially solid core, as defined herein.
In one embodiment, the invention provides a lipid nanoparticle comprising a transfection reagent composition and a nucleic acid. The nucleic acid can be a DNA, a RNA, a locked nucleic acid, a nucleic acid analog, or a plasmid capable of expressing a DNA or an RNA.
In another embodiment, the invention provides a lipid nanoparticle comprising a transfection reagent composition and an antisense oligonucleotide hybridization probe. The hybridization probe can be a molecular beacon.
In another aspect, the invention provides a lipid nanoparticle comprising (a) one or more cationic lipids, (b) one or more second lipids, (c) one or more sterols, and (d) one or more surfactants and one or more nucleic acids as defined herein. In one embodiment, the cationic lipid is 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate. In one embodiment, the second lipid is 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC). In one embodiment, the sterol lipid is cholesterol. In one embodiment, the surfactant is polyoxyethylene (20) oleyl ether. In one embodiment the nucleic acid is a siRNA.
In another aspect, the invention provides a lipid nanoparticle comprising (a) one or more cationic lipids, (b) one or more second lipids, (c) one or more sterols, and (d) one or more surfactants and one or more nucleic acids as defined herein. In one embodiment, the cationic lipid is 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate. In one embodiment, the second lipid is 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC). In one embodiment, the sterol lipid is cholesterol. In one embodiment, the surfactant is polyoxyethylene (40) stearate. In one embodiment the nucleic acid is a siRNA.
In another aspect, the invention provides a lipid nanoparticle comprising (a) one or more cationic lipids, (b) one or more second lipids, (c) one or more sterols, and (d one or more surfactants and one or more nucleic acids as defined herein. In one embodiment, the cationic lipid is 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl 4-(dimethylamino)butanoate. In one embodiment, the second lipid is 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC). In one embodiment, the sterol lipid is cholesterol. In one embodiment, the surfactant is polyoxyethylene (20) oleyl ether. In one embodiment the nucleic acid is a plasmid DNA.
In another aspect, the invention provides a lipid nanoparticle comprising (a) one or more cationic lipids, (b) one or more second lipids, (c) one or more sterols, and (d) one or more surfactants and one or more nucleic acids as defined herein. In one embodiment, the cationic lipid is 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate. In one embodiment, the second lipid is 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC). In one embodiment, the sterol lipid is cholesterol. In one embodiment, the surfactant is polyoxyethylene (40) stearate. In one embodiment the nucleic acid is a plasmid DNA.
In one embodiment, the invention provides a method for administering a nucleic acid to a subject, comprising administering a lipid nanoparticle of the invention to a subject in need thereof.
In one embodiment, the invention provides a method for introducing a nucleic acid into a cell, comprising contacting a cell with the lipid nanoparticle of the invention.
In one embodiment, the invention provides a method for modulating the expression of a target polynucleotide or polypeptide, comprising contacting a cell with the lipid nanoparticle of the invention, wherein the nucleic acid capable of modulating the expression of a target polynucleotide or polypeptide.
In one embodiment, the invention provides a method of treating a disease or disorder characterized by overexpression of a polypeptide in a subject, comprising administering to the subject the lipid nanoparticle of the invention, wherein the nucleic acid capable of silencing or decreasing the expression of the polypeptide.
In one embodiment, the invention provides a method of treating a disease or disorder characterized by the absence of expression, or under expression, of a polypeptide in a subject, comprising administering to the subject the lipid nanoparticle of the invention, wherein the nucleic acid capable of expressing or increasing the expression of the polypeptide.
In other aspect, the invention provides a method for making lipid nanoparticles.
In one embodiment, the invention provides a method for making lipid nanoparticles containing a nucleic acid, comprising:
(a) introducing a first stream comprising a nucleic acid in a first solvent into a microfluidic device; wherein the device has a first region adapted for flowing one or more streams introduced into the device and a second region for mixing the contents of the one or more streams with a microfluidic mixer;
(b) introducing a second stream comprising transfection reagent composition in a second solvent into the device, wherein the device has a first region adapted for flowing one or more streams introduced into the microchannel and directing them into a second region for mixing the contents of the one or more streams, wherein the transfection reagent composition comprise a cationic lipid, and wherein the first and second solvents are not the same;
(c) flowing the one or more first streams and the one or more second streams from the first region of the device into the second region of the device; and
(d) mixing of the contents of the one or more first streams and the one or more second streams in the second region of the device to provide a third stream comprising lipid nanoparticles with encapsulated nucleic acid.
In another embodiment, the invention provides a method for making lipid nanoparticles containing a nucleic acid, comprising:
(a) introducing a first stream comprising a nucleic acid in a first solvent into a channel; wherein the device has a first region adapted for flowing one or more streams introduced into the channel and a second region for mixing the contents of the one or more streams;
(b) introducing a second stream comprising transfection reagent composition in a second solvent; wherein the channel has a first region adapted for flowing one or more streams introduced into the channel and a second region for mixing the contents of the one or more streams;
(c) flowing the one or more first streams and the one or more second streams from the first region of the channel into the second region of the channel, while maintaining a physical separation of the two streams, wherein the one or more first streams and the one or more second streams do not mix until arriving at the second region of the channel; and
(d) mixing of the contents of the one or more first streams and the one or more second streams flowing in the second region of the microchannel to provide a third stream comprising lipid nanoparticles with encapsulated nucleic acids.
In certain embodiments of the above methods, mixing the contents of the one or more first streams and the one or more second streams comprises varying the concentration or relative mixing rates of the one or more first streams and the one or more second streams.
In certain embodiments of the above methods, the methods further comprise diluting the third stream with an aqueous buffer. In certain embodiments, diluting the third stream comprises flowing the third stream and an aqueous buffer into a second mixing structure.
In certain embodiments of the above methods, the methods further comprise dialyzing the aqueous buffer comprising lipid nanoparticles with encapsulated nucleic acids to reduce the amount of the second solvent.
In certain embodiments of the above methods, the first solvent is an aqueous buffer. In certain embodiments of the above methods, the second solvent is an aqueous alcohol.
In certain embodiments of the above methods, mixing the contents of the first and second streams comprises chaotic advection. In certain embodiments of the above methods, mixing the contents of the first and second streams comprises mixing with a micromixer.
In certain embodiments of the above methods, the nucleic acid encapsulation efficiency is from about 80 to about 100%.
In certain embodiments of the above methods, mixing of the one or more first streams and the one or more second streams is prevented in the first region by a barrier. In certain embodiments, the barrier is a channel wall, sheath fluid, or concentric tubing.
In another aspect of the invention, devices for making lipid nanoparticles are provided. In one embodiment, the invention provides a device for producing a lipid nanoparticle encapsulating a nucleic acid, comprising:
(a) a first inlet for receiving a first solution comprising a nucleic acid in a first solvent;
(b) a first inlet microchannel in fluid communication with the first inlet to provide a first stream comprising the nucleic acid in the first solvent;
(c) a second inlet for receiving a second solution comprising transfection reagent composition in a second solvent;
(d) a second inlet microchannel in fluid communication with the second inlet to provide a second stream comprising the transfection reagent composition in the second solvent; and
(e) a third microchannel for receiving the first and second streams, wherein the third microchannel has a first region adapted for flowing the first and second streams introduced into the microchannel and a second region adapted for mixing the contents of the first and second streams to provide a third stream comprising lipid nanoparticles with encapsulated nucleic acid.
In one embodiment, the device further comprises means for diluting the third stream to provide a diluted stream comprising stabilized lipid nanoparticles with encapsulated nucleic acid. In certain embodiments, the means for diluting the third stream comprises a micromixer.
In one embodiment, the microchannel has a hydrodynamic diameter from about 20 to about 300 μm.
In one embodiment, the second region of the microchannel comprises bas-relief structures. In one embodiment, the second region of the microchannel has a principal flow direction and one or more surfaces having at least one groove or protrusion defined therein, the groove or protrusion having an orientation that forms an angle with the principal direction. In one embodiment, the second region comprises a micromixer.
In certain embodiments, the device further comprises means for varying the flow rates of the first and second streams.
In certain embodiments, the device further comprises a barrier effective to physically separate the one or more first streams from the one or more second streams in the first region.

DESCRIPTION OF THE DRAWINGS

The foregoing aspects and many of the attendant advantages of this invention will become more readily appreciated as the same become better understood by reference to the following detailed description, when taken in conjunction with the accompanying drawings.

FIG. 1 uses the Factor VII (FVII) Mouse Model to illustrate the in vivo silencing activity of siRNA-LNP prepared with different surfactants (polyoxyethylene (40) stearate (Myrj S40), polyoxyethylene (20) oleyl ether (Brij 98) Brij 35P-polyoxyethylene (23) lauryl ether (Brij 35P)). siRNA-LNP were manufactured using the microfluidic method. Activity was measured as percent Residual FVII protein level as a function of mole percent (mol %) of surfactant used in the siRNA-LNP formulation. All LNP consisted of the following lipid composition according to the formula: 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate:DSPC:Cholesterol:Surfactant (50%:10%:40%-% Surfactant:% Surfactant). siRNA-LNP-to-lipid ratio was 0.06 weight/weight. Mice (n=3) were injected via the tail vein with a single dose equivalent to 1 mg/kg siRNA. Blood collection was performed 24 hours post-injection and FVII levels were determined by colorimetric assay. The data indicates that FVII levels in the blood were reduced by >95% compared to control 24 hours after a single intravenous injection of siRNA-LNP at a siRNA dose of 1 mg/kg. This observation was independent of the surfactant used, or the mol % surfactant incorporated into the siRNA-LNP.

FIG. 2 uses the Factor VII (FVII) Mouse Model to illustrate the in vivo silencing activity of siRNA-LNP prepared with the surfactant polyoxyethylene (40) stearate. siRNA-LNP were manufactured using the microfluidic method. Activity was measured as percent Residual FVII protein level as a function of siRNA dose and time. All LNP comprised: 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate:DSPC:Cholesterol:polyoxyethylene (40) stearate (50:10:37.5:2.5 mol %). siRNA-LNP-to-lipid ratio was 0.06 weight/weight. Mice (n=3) were injected via the tail vein with a single dose equivalent to 0.01, 0.05, 0.1, 0.3, 0.5 and 1 mg/kg siRNA. Blood collection was performed at days 1, 7, 14 and 21 post-injection and FVII levels were determined by colorimetric assay. The data indicates that FVII levels in the blood were reduced by >95% compared to for at least 7 days after a single intravenous injection of siRNA-LNP at a siRNA dose of 1 mg/kg.

FIG. 3 uses the Factor VII (FVII) Mouse Model to illustrate the in vivo silencing activity of siRNA-LNP prepared with the surfactant polyoxyethylene (20) oleyl ether. siRNA-LNP were manufactured using the microfluidic method. Activity was measured as percent Residual FVII protein level as a function of siRNA dose and time. All LNP comprised: 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4(dimethylamino)butanoate:DSPC:Cholesterol:Polyoxyethylene (20) oleyl ether (50:10:38:2 mol %). siRNA-LNP-to-lipid ratio was 0.06 weight/weight. Mice (n=3) were injected via the tail vein with a single dose equivalent to 0.01, 0.05, 0.1, 0.3, 0.5 and 1 mg/kg siRNA. Blood collection was performed at days 1, 7, 14 and 21 post-injection and FVII levels were determined by colorimetric assay. The data indicates that FVII levels in the blood were reduced by >95% compared to for at least 7 days after a single intravenous injection of siRNA-LNP at a siRNA dose of >0.5 mg/kg.

FIG. 4 uses the Factor VII (FVII) Mouse Model to illustrate the in vivo silencing activity of siRNA-LNP prepared with the surfactant polyoxyethylene (23) lauryl ether. siRNA-LNP were manufactured using the microfluidic method. Activity was measured as percent Residual FVII protein level as a function of siRNA dose and time. All LNP comprised: 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate:DSPC:Cholesterol:polyoxyethylene (23) lauryl ether(50:10:38:2 mol %). siRNA-LNP-to-lipid ratio was 0.06 wt/wt. Mice (n=3) were injected via the tail vein with a single dose equivalent to 0.01, 0.05, 0.1, 0.3, 0.5 and 1 mg/kg siRNA. Blood collection was performed at days 1, 7, 14 and 21 post-injection and FVII levels were determined by colorimetric assay. The data indicates that FVII levels in the blood were reduced by >95% compared to for at least 7 days after a single intravenous injection of siRNA-LNP at a siRNA dose of >0.5 mg/kg.

FIG. 5 is a schematic illustration of a representative microfluidic (MF) method of the invention for making lipid nanoparticles (LNP): Lipid-ethanol and siRNA-aqueous solutions are pumped into inlets of a microfluidic mixing device; herringbone features in the device induce chaotic advection of the stream and cause the lipid species to rapidly mix with the aqueous stream and form lipid nanoparticles. The mixing channel is 300 μm wide and 130 μm high. The herringbone structures are 40 μm high and 53 μm thick.

FIG. 6 is a table that summarizes Z-Ave and PDI for representative lipid nanoparticles prepared from transfection reagent compositions of the invention.

FIG. 7 is a table that summarizes nucleic acid encapsulation efficiency for representative lipid nanoparticles prepared from transfection reagent compositions of the invention.

FIG. 8 is a schematic illustration of a representative device and method of the invention for preparing particles at small volumes: a device that uses a combination of input and output reservoirs (wells) to control flow rates and flow timing. In this device, input wells are used to contain input fluids. Channel impedances are used to determine the relative flow rates between flows from the inputs. An outlet well is added. In certain embodiments, a backpressure or stopper is applied to the outlet well to stop fluidic movement from the inputs due to the weight of fluids in the input wells or other phenomena, prior to a pressure applied to the inputs. In certain embodiments, a backpressure is achieved by adding fluid to the outlet well prior to adding fluids to the input wells. In this case fluids with the lowest surface tension are added last because these are the fluids which move through the chip at the highest rate. The input fluids are then added into the input reservoirs and the inputs are pressurized to create fluid flow. Flow rates of the different flows are controlled by the impedances of the channels from the inputs to the mixer chamber. The flows can be timed to reach the mixer at a similar time by pressurizing the input wells simultaneously. In certain embodiments, the device is purged of remaining fluid by applying fluid (gas or liquid) to the inputs and flowed through the mixers following nanoparticle manufacture.

FIG. 9 is an example of a representative device illustrated in the schematic of FIG. 8. This device has two inlet wells (one for an aqueous phase and one for an ethanol/lipid phase) and one outlet well. In practice, a dilution buffer is loaded into the outlet well, this buffer adds backpressure at the output of the device and lowers the ethanol concentration of the final product which stabilizes the particles. Aqueous reagents and lipids in ethanol are loaded into the input wells, a manifold is then clamped oven the inlet wells and pressurized using a syringe or other mechanism. The pressurization pushes the reagents in the inlet wells through the mixer (e.g., a staggered herringbone mixer) and into the outlet well. The formulated particles are then recovered using a pipette. The shown device is designed to have a flow ratio of 3 parts aqueous to 1 part ethanol, which is achieved with different channel lengths leading from the input wells to them mixer. In this case, the ratio of 2.5:1 is used and this takes into account the desired flow ratio and the viscosity difference between the input reagents.

FIG. 10 is a schematic illustration of a representative device and method of the invention for preparing particles at small volumes: a device that flows a first stream of solvent (input wells 1 through n) into a second solvent contained in the outlet reservoir (dilution well). Mixing of the first stream with the contents of the outlet reservoir can occur through various mechanisms including (i) convection flows occurring by introducing the first stream into the reservoir and (ii) active mixing of the combined fluids as the first stream is introduced into the reservoir.

FIG. 11 is an example of a representative device illustrated in the schematic of FIG. 10. The device has a single input well for a lipid/ethanol solution and an outlet well into which an aqueous solution is loaded. The device has a large number of microchannels leading into the outlet well, the impedance of microchannels is high compared to the channel feeding them. This is necessary for an even distribution of fluid. After the reagents are loaded, the inlet well is pressurized. The fluid in the inlet well flows through the microchannels and into the output well. The fluid is mixed by convection and by air bubbles flowing into the outlet well.

FIG. 12 is a schematic illustration of a representative device and method of the invention for preparing particles at small volumes: a device using valves either at the inlets or outlet to time the introduction of fluidic flows into the mixing chamber.

DETAILED DESCRIPTION OF THE INVENTION

The present invention provides a transfection reagent composition, lipid nanoparticles containing anionic macromolecule(s), methods and devices for making the lipid nanoparticles containing anionic macromolecule(s) using the transfection reagent composition, and methods for transfecting a cell using the lipid nanoparticles.
Transfection Reagent Composition
In one aspect, the invention provides a transfection reagent composition. The transfection reagent composition includes one or more cationic lipids, one or more second lipids, one or more sterols and one or more surfactants.
Lipid Nanoparticles
In one aspect, the invention provides lipid nanoparticles containing anionic macromolecule(s). The lipid nanoparticles include one or more cationic lipids, one or more second lipids, and one or more nucleic acids.
Cationic Lipids
The lipid nanoparticles include a cationic lipid. As used herein, the term “cationic lipid” refers to a lipid that is cationic or becomes cationic (protonated) as the pH is lowered below the pK of the ionizable group of the lipid, but is progressively more neutral at higher pH values. At pH values below the pK, the lipid is then able to associate with negatively charged nucleic acids (e.g., oligonucleotides). As used herein, the term “cationic lipid” includes zwitterionic lipids that assume a positive charge on pH decrease. Cationic lipids useful in the invention do not include PEG-phospholipids (e.g., polyethylene oxide-containing phospholipids).
The term “cationic lipid” refers to any of a number of lipid species which carry a net positive charge at a selective pH, such as physiological pH. Such lipids include, but are not limited to, N,N-dioleyl-N,N-dimethylammonium chloride (DODAC); N-(2,3-dioleyloxy)propyl)-N,N,N-trimethylammonium chloride (DOTMA); N,N-distearyl-N,N-dimethylammonium bromide (DDAB); N-(2,3-dioleoyloxy)propyl)-N,N,N-trimethylammonium chloride (DOTAP); 3-(N—(N′,N′-dimethylaminoethane)-carbamoyl)cholesterol (DC-Chol); and N-(1,2-dimyristyloxyprop-3-yl)-N,N-dimethyl-N-hydroxyethyl ammonium bromide (DMRIE). Additionally, a number of commercial preparations of cationic lipids are available which can be used in the present invention. These include, for example, LIPOFECTIN® (commercially available cationic liposomes comprising DOTMA and 1,2-dioleoyl-sn-3-phosphoethanolamine (DOPE), from GIBCO/BRL, Grand Island, N.Y.); LIPOFECTAMINE® (commercially available cationic liposomes comprising N-(1-(2,3-dioleyloxy)propyl)-N-(2-(sperminecarboxamido)ethyl)-N,N-dimethyl-ammonium trifluoroacetate (DOSPA) and (DOPE), from GIBCO/BRL); and TRANSFECTAM® (commercially available cationic lipids comprising dioctadecylamidoglycylcarboxyspermine (DOGS) in ethanol from Promega Corp., Madison, Wis.). The following lipids are cationic and have a positive charge at below physiological pH: DODAP, DODMA, DMDMA, 1,2-dilinoleyloxy-N,N-dimethylaminopropane (DLinDMA), 1,2-dilinolenyloxy-N,N-dimethylaminopropane (DLenDMA), 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino) butanoate (referred to here as “Cationic Lipid A”).
In one embodiment, the cationic lipid is an amino lipid (or a pharmaceutically acceptable salts thereof (e.g., hydrochloride salt)). Suitable amino lipids useful in the invention include those described in WO 2012/016184, incorporated herein by reference in its entirety. Representative amino lipids include 1,2-dilinoleyoxy-3-(dimethylamino)acetoxypropane (DLin-DAC), 1,2-dilinoleyoxy-3-morpholinopropane (DLin-MA), 1,2-dilinoleoyl-3-dimethylaminopropane (DLinDAP), 1,2-dilinoleylthio-3-dimethylaminopropane (DLin-S-DMA), 1-linoleoyl-2-linoleyloxy-3-dimethylaminopropane (DLin-2-DMAP), 1,2-dilinoleyloxy-3-trimethylaminopropane chloride salt (DLin-TMA.Cl), 1,2-dilinoleoyl-3-trimethylaminopropane chloride salt (DLin-TAP.Cl), 1,2-dilinoleyloxy-3-(N-methylpiperazino)propane (DLin-MPZ), 3-(N,N-dilinoleylamino)-1,2-propanediol (DLinAP), 3-(N,N-dioleylamino)-1,2-propanediou (DOAP), 1,2-dilinoleyloxo-3-(2-N,N-dimethylamino)ethoxypropane (DLin-EG-DMA), and 2,2-dilinoleyl-4-dimethylaminomethyl-[1,3]-dioxolane (DLin-K-DMA), and pharmaceutically acceptable salts thereof (e.g., hydrochloride salts).
Suitable amino lipids include those having the formula:
or a pharmaceutically acceptable salt thereof (e.g., hydrochloride salt),
wherein R₁and R₂are either the same or different and independently optionally substituted C10-C24 alkyl, optionally substituted C10-C24 alkenyl, optionally substituted C10-C24 alkynyl, or optionally substituted C10-C24 acyl;
R₃and R₄are either the same or different and independently optionally substituted C1-C6 alkyl, optionally substituted C2-C6 alkenyl, or optionally substituted C2-C6 alkynyl or R₃and R₄may join to form an optionally substituted heterocyclic ring of 4 to 6 carbon atoms and 1 or 2 heteroatoms chosen from nitrogen and oxygen;
R₅is either absent or present and when present is hydrogen or C1-C6 alkyl;
m, n, and p are either the same or different and independently either 0 or 1 with the proviso that m, n, and p are not simultaneously 0;
q is 0, 1, 2, 3, or 4; and
Y and Z are either the same or different and independently O, S, or NH.
In another embodiment, the cationic lipid has the formula:
or a pharmaceutically acceptable salt thereof (e.g., hydrochloride), wherein:
R₁and R₂are each independently H, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, and heterocyclyl,
wherein each of alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, and heterocyclyl is optionally substituted by H; halo; hydroxy; cyano; oxo; C₁-C₆alkyl optionally substituted by halo, hydroxy, or alkoxy;
or R₁and R₂are taken together with the N atom to which they are both attached to form a 3-8 member heteroaryl or heterocyclyl; wherein each of the heteroaryl and heterocyclyl is optionally substituted by H; halo; hydroxy; cyano; oxo; nitro; C₁-C₆alkyl optionally substituted by halo, hydroxyl, or alkoxy;
R₃is absent, H, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, or heterocyclyl;
R₄and R₅are each independently H, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, or heterocyclyl;
wherein each of alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, and heterocyclyl is optionally substituted by H; halo; hydroxy; cyano; oxo; C₁-C₆alkyl optionally substituted by halo, hydroxy, or alkoxy;
X is —O—, —S—, —NR₄—, —S—S—, —OC(═O)—, —C(═O)O—, —OC(═O)O—, —NR₄C(═O)—, C(═O)NR₄—, —NR₄C(═O)O—, —OC(═O)NR₄—, —NR₄C(═O)NR₄—, —NR₄C(═S)O—, OC(═S)NR₄—, —NR₄C(═S)NR₄—, —CR₄R₅—;
Y and Z are independently C₁₀to C₃₀groups having the formula L₁-(CR₆R₇)_α-[L₂-(CR₆R₇)_β]_γ-L₃-R₈, wherein
L₁is a bond, —(CR₆R₇)—, —O—, —CO—, —NR₈—, —S—, or a combination thereof;
each R₆and R₇, independently, is H; halo; hydroxyl, cyano; C₁-C₆alkyl optionally substituted by halo, hydroxyl, or alkoxy:
L₂is a bond, —(CR₆R₇)—, —O—, —CO—, —NR₈—, —S—,
or a combination thereof, or has the formula
wherein b, c, and d are each independently 0, 1, 2, or 3, given the sum of b, c, and d is at least 1 and no greater than 8; and R₉and R₁₀are each independently R₇, or adjacent R₉and R₁₀, taken together, are optionally a bond;
or a combination thereof;
R₈is independently H; halo; hydroxy; cyano; C1-C6 alkyl optionally substituted by halo, hydroxy, or alkoxy; aryl; heteroaryl; or heterocyclyl; or R₈has the formula:
a is 0, 1, 2, 3, or 4;
α is 0-6;
each β, independently, is 0-6;
γ is 0-6.
Other suitable cationic lipids include cationic lipids, which carry a net positive charge at about physiological pH, in addition to those specifically described above, N,N-dioleyl-N,N-dimethylammonium chloride (DODAC); N-(2,3-dioleyloxy)propyl-N,N—N-triethylammonium chloride (DOTMA); N,N-di stearyl-N,N-dimethylammonium bromide (DDAB); N-(2,3-dioleoyloxy)propyl)-N,N,N-trimethylammonium chloride (DOTAP); 1,2-dioleyloxy-3-trimethylaminopropane chloride salt (DOTAP.Cl); 3β-(N—(N′,N′-dimethylaminoethane)carbamoyl)cholesterol (DC-Chol), N-(1-(2,3-dioleoyloxy)propyl)-N-2-(sperminecarboxamido)ethyl)-N,N-dimethylammoniumtrifluoracetate (DOSPA), dioctadecylamidoglycylcarboxyspermine (DOGS), 1,2-dioleoyl-3-dimethylammonium propane (DODAP), N,N-dimethyl-2,3-dioleoyloxy)propylamine (DODMA), and N-(1,2-dimyristyloxyprop-3-yl)-N,N-dimethyl-N-hydroxyethyl ammonium bromide (DMRIE). Additionally, a number of commercial preparations of cationic lipids can be used, such as, e.g., LIPOFECTIN (including DOTMA and DOPE, available from GIBCO/BRL), and LIPOFECTAMINE (comprising DOSPA and DOPE, available from GIBCO/BRL).
The cationic lipid is present in the transfection reagent composition in an amount from about 30 to about 95 mole percent. In one embodiment, the cationic lipid is present in the transfection reagent composition in an amount from about 30 to about 70 mole percent. In one embodiment, the cationic lipid is present in the transfection reagent composition in an amount from about 40 to about 60 mole percent.
Neutral Lipids
In certain embodiments, the transfection reagent composition includes one or more neutral lipids.
The term “lipid” refers to a group of organic compounds that are esters of fatty acids and are characterized by being insoluble in water but soluble in many organic solvents. Lipids are usually divided in at least three classes: (1) “simple lipids” which include fats and oils as well as waxes; (2) “compound lipids” which include phospholipids and glycolipids; and (3) “derived lipids” such as steroids.
The term “neutral lipid” refers to any one of a number of lipid species that exist in either an uncharged or neutral zwitterionic form at physiological pH. Neutral lipids useful in the invention do not include PEG-phospholipids (e.g. polyethylene oxide-containing phospholipids). Representative neutral lipids include diacylphosphatidylcholines, diacylphosphatidylethanolamines, ceramides, sphingomyelins, dihydrosphingomyelins, cephalins, and cerebrosides.
Exemplary lipids include, for example, distearoylphosphatidylcholine (DSPC), dioleoylphosphatidylcholine (DOPC), dipalmitoylphosphatidylcholine (DPPC), dioleoylphosphatidylglycerol (DOPG), dipalmitoylphosphatidylglycerol (DPPG), dioleoyl-phosphatidylethanolamine (DOPE), palmitoyloleoylphosphatidylcholine (POPC), palmitoyloleoyl-phosphatidylethanolamine (POPE) and dioleoyl-phosphatidylethanolamine 4-(N-maleimidomethyl)-cyclohexane-1-carboxylate (DOPE-mal), dipalmitoylphosphatidyl ethanolamine (DPPE), dimyristoylphosphoethanolamine (DMPE), distearoyl-phosphatidylethanolamine (DSPE), 16-O-monomethyl PE, 16-O-dimethyl PE, 18-1-trans PE, 1-stearioyl-2-oleoyl-phosphatidyethanol amine (SOPE), and 1,2-dielaidoyl-sn-glycero-3-phophoethanolamine (transDOPE).
In one embodiment, the neutral lipid is 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC).
Sterols
In certain embodiments, the transfection reagent composition includes one or more sterols.
The term “sterol” refers to a subgroup of steroids also known as steroid alcohols.
Sterols are usually divided into two classes: (1) plant sterols also known as “phytosterols”; and (2) animal sterols also known as “zoosterols.”
Exemplary sterols include, for example, campesterol, sitosterol, stigmasterol, ergosterol and chloesterol.
In one embodiment, the sterol is cholesterol.
Surfactants
In certain embodiments, the transfection reagent composition includes one or more surfactants.
The term surfactant as used herein, refers to non-ionic, amphipathic compounds that contain both hydrophobic groups and hydrophilic groups. Surfactants useful in the invention do not include PEG-phospholipids (e.g. polyethylene oxide-containing phospholipids).
In one embodiment, a surfactant is represented by the formula
wherein
R₁is H, C₁-C₆alkyl;
X is-O—, —S—, —NR₂—, —S—S—, —OC(═O)—, —C(═O)O—, —OC(═O)O—, —NR₂C(═O)—, C(═O)NR₂—, —NR₂C(═O)O—, —OC(═O)NR₂—, —NR₂C(═O)NR₂—, —NR₂C(═S)O—, OC(═S)NR₂—, —NR₂C(═S)NR₂—, —CR₂R₃—;
R₂and R₃are each independently H, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, or heterocyclyl;
wherein each of alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, and heterocyclyl is optionally substituted by H; halo; hydroxy; cyano; oxo; C₁-C₆alkyl optionally substituted by halo, hydroxy, or alkoxy;
Y is a C₁₀to C₄₀group having the formula L₁-(CR₄R₅)_α-[L₂-(CR₄R₅)_β]γ-L₃-R₆, wherein:
L₁is a bond, —(CR₄R₅)—, —O—, —CO—, —NR₂—, —S—, or a combination thereof; each R₄and R₅, independently, is H; halo; hydroxyl, cyano; C₁-C₆alkyl optionally substituted by halo, hydroxyl, or alkoxy;
L₂and L₃each, independently, are a bond, —(CR₄R₅)—, —O—, —CO—, —NR₂—, —S—,
or a combination thereof;
R₆is independently H; halo; hydroxy; cyano; C₁-C₆alkyl optionally substituted by halo, hydroxy, or alkoxy; aryl; heteroaryl; or heterocyclyl; or R₆has the formula:
a is 2-100;
α is 0-6;
each β, independently, is 0-6;
γ is 0-6.
In another embodiment, a surfactant is represented by the formula
wherein:
x=1 to 50;
y=1 to 50; and
z=1 to 50.
In another embodiment, a surfactant is represented by the formula
wherein:
x=1 to 50;
y=1 to 50; and
z=1 to 50.
In certain embodiments, the surfactant is selected from the group consisting of polyoxyethylene alkyl ethers, polyoxyethylene alkyl esters, diblock polyoxyethylene alkyl ether co-polymers and triblock polyoxyethylene alkyl ether co-polymers. Suitable surfactants include polyoxyethylene (20) oleyl ether, polyoxyethylene (23) lauryl ether, polyoxyethylene (40) stearate, poly(propylene glycol)₁₁-block-poly(ethylene glycol)₁₆-block-poly(propylene glycol)₁₁, poly(propylene glycol)₁₂-block-poly(ethylene glycol)₂₈-block-poly(propylene glycol)₁₂.
In certain embodiments, the surfactant is present in the transfection reagent composition in an amount from about 0.1 to about 20 mole percent. In one embodiment, the surfactant is present in the transfection reagent composition in an amount from about 0.5 to about 10 mole percent. In one embodiment, the surfactant is present in the lipid nanoparticle in about 2 mole percent.
In one embodiment, the surfactant is polyoxyethylene (20) oleyl ether.
In one embodiment, the surfactant is polyoxyethylene (40) stearate.
In one embodiment, the transfection reagent composition includes:
(a) a cationic lipid that is an aminolipid or a pharmaceutically acceptable salt thereof;
(b) a neutral lipid that is a phospholipid;
(c) a sterol that is cholesterol; and
(d) a surfactant that is selected from polyoxyethylene (20) oleyl ether, polyoxyethylene (23) lauryl ether, or polyoxyethylene (40) stearate.
In another embodiment, the transfection reagent composition includes:
(a) a cationic lipid that is 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate or a pharmaceutically acceptable salt thereof;
(b) a neutral lipid that is 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC);
(c) a sterol that is cholesterol; and
(d) a surfactant that is selected from polyoxyethylene (20) oleyl ether, polyoxyethylene (23) lauryl ether, or polyoxyethylene (40) stearate.
In certain embodiments, the transfection reagent compositions of the invention do not include PEG-phospholipids (e.g. polyethylene oxide-containing phospholipids).
Anionic Macromolecules
The lipid nanoparticles of the present invention are useful for the systemic or local delivery of anionic macromolecules. As described herein, the transfection reagent composition is mixed with the anionic macromolecule which is incorporated into the resulting lipid nanoparticle.
As used herein, the term “anionic macromolecule” refers to a macromolecule that is anionic or becomes anionic (deprotonated) as the pH is increased above the pK of the ionizable group of the macromolecule, but is progressively more neutral at lower pH values. At pH values above the pK, the macromolecule is then able to associate with positively charged lipids (e.g., cationic lipids). As used herein, the term “anionic macromolecule” includes zwitterionic macromolecules that assume a negative charge on pH increase.
The term “anionic macromolecule” refers to any of a number of species which carry a net negative charge at a selective pH, such as physiological pH. Such macromolecules include, but are not limited to, nucleic acids, proteins, peptides and carbohydrates.
Nucleic Acids
The lipid nanoparticles of the present invention are useful for the systemic or local delivery of nucleic acids. As described herein, the transfection reagent composition is mixed with the nucleic acid which is incorporated into the resulting lipid nanoparticle.
As used herein, the term “nucleic acid” is meant to include any oligonucleotide or polynucleotide. Fragments containing up to 50 nucleotides are generally termed oligonucleotides, and longer fragments are called polynucleotides. In particular embodiments, oligonucleotides of the present invention are 20-50 nucleotides in length. In the context of this invention, the terms “polynucleotide” and “oligonucleotide” refer to a polymer or oligomer of nucleotide or nucleoside monomers consisting of naturally occurring bases, sugars and intersugar (backbone) linkages. The terms “polynucleotide” and “oligonucleotide” also includes polymers or oligomers comprising non-naturally occurring monomers, or portions thereof, which function similarly. Such modified or substituted oligonucleotides are often preferred over native forms because of properties such as, for example, enhanced cellular uptake and increased stability in the presence of nucleases. Oligonucleotides are classified as deoxyribooligonucleotides or ribooligonucleotides. A deoxyribooligonucleotide consists of a 5-carbon sugar called deoxyribose joined covalently to phosphate at the 5′ and 3′ carbons of this sugar to form an alternating, unbranched polymer. A ribooligonucleotide consists of a similar repeating structure where the 5-carbon sugar is ribose. The nucleic acid that is present in a lipid nanoparticle according to this invention includes any form of nucleic acid that is known. The nucleic acids used herein can be single-stranded DNA or RNA, or double-stranded DNA or RNA, or DNA-RNA hybrids. Examples of double-stranded DNA include structural genes, genes including control and termination regions, and self-replicating systems such as viral or plasmid DNA. Examples of double-stranded RNA include siRNA and other RNA interference reagents. Single-stranded nucleic acids include antisense oligonucleotides, ribozymes, microRNA, and triplex-forming oligonucleotides.
In one embodiment, the polynucleic acid is an antisense oligonucleotide. In certain embodiments, the nucleic acid is an antisense nucleic acid, a ribozyme, tRNA, snRNA, siRNA, shRNA, ncRNA, miRNA, pre-condensed DNA, or an aptamer.
The term “nucleic acids” also refers to ribonucleotides, deoxynucleotides, modified ribonucleotides, modified deoxyribonucleotides, modified phosphate-sugar-backbone oligonucleotides, other nucleotides, nucleotide analogs, and combinations thereof, and can be single stranded, double stranded, or contain portions of both double stranded and single stranded sequence, as appropriate.
The term “nucleotide,” as used herein, generically encompasses the following terms, which are defined below: nucleotide base, nucleoside, nucleotide analog, and universal nucleotide.
The term “nucleotide base,” as used herein, refers to a substituted or unsubstituted parent aromatic ring or rings. In some embodiments, the aromatic ring or rings contain at least one nitrogen atom. In some embodiments, the nucleotide base is capable of forming Watson-Crick and/or Hoogsteen hydrogen bonds with an appropriately complementary nucleotide base. Exemplary nucleotide bases and analogs thereof include, but are not limited to, purines such as 2-aminopurine, 2,6-diaminopurine, adenine (A), ethenoadenine, N6-2-isopentenyladenine (6iA), N6-2-isopentenyl-2-methylthioadenine (2 ms6iA), N6-methyladenine, guanine (G), isoguanine, N2-dimethylguanine (dmG), 7-methylguanine (7mG), 2-thiopyrimidine, 6-thioguanine (6sG) hypoxanthine and 06-methylguanine; 7-deaza-purines such as 7-deazaadenine (7-deaza-A) and 7-deazaguanine (7-deaza-G); pyrimidines such as cytosine (C), 5-propynylcytosine, isocytosine, thymine (T), 4-thiothymine (4sT), 5,6-dihydrothymine, O4-methylthymine, uracil (U), 4-thiouracil (4sU) and 5,6-dihydrouracil (dihydrouracil; D); indoles such as nitroindole and 4-methylindole; pyrroles such as nitropyrrole; nebularine; base (Y); in some embodiments, nucleotide bases are universal nucleotide bases. Additional exemplary nucleotide bases can be found in Fasman, 1989, Practical Handbook of Biochemistry and Molecular Biology, pp. 385-394, CRC Press, Boca Raton, Fla., and the references cited therein. Further examples of universal bases can be found, for example, in Loakes, N. A. R. 2001, 29:2437-2447, and Seela N. A. R. 2000, 28:3224-3232.
The term “nucleoside,” as used herein, refers to a compound having a nucleotide base covalently linked to the C-1′ carbon of a pentose sugar. In some embodiments, the linkage is via a heteroaromatic ring nitrogen. Typical pentose sugars include, but are not limited to, those pentoses in which one or more of the carbon atoms are each independently substituted with one or more of the same or different —R, —OR, —NRR or halogen groups, where each R is independently hydrogen, (C1-C6) alkyl or (C5-C14) aryl. The pentose sugar may be saturated or unsaturated. Exemplary pentose sugars and analogs thereof include, but are not limited to, ribose, 2′-deoxyribose, 2′-(C1-C6)alkoxyribose, 2′-(C5-C14)aryloxyribose, 2′,3′-dideoxyribose, 2′,3′-didehydroribose, 2′-deoxy-3′-haloribose, 2′-deoxy-3′-fluororibose, 2′-deoxy-3′-chlororibose, 2′-deoxy-3′-aminoribose, 2′-deoxy-3′-(C1-C6)alkylribose, 2′-deoxy-3′-(C1-C6)alkoxyribose and 2′-deoxy-3′-(C5-C14)aryloxyribose. Also see, e.g., 2′—O-methyl, 4′-α-anomeric nucleotides, 1′-α-anomeric nucleotides (Asseline (1991) Nucl. Acids Res. 19:4067-74), 2′-4′- and 3′-4′-linked and other “locked” or “LNA,” bicyclic sugar modifications (WO 98/22489; WO 98/39352; WO 99/14226). “LNA” or “locked nucleic acid” is a DNA analogue that is conformationally locked such that the ribose ring is constrained by a methylene linkage between the 2′-oxygen and the 3′- or 4′-carbon. The conformation restriction imposed by the linkage often increases binding affinity for complementary sequences and increases the thermal stability of such duplexes.
Sugars include modifications at the 2′- or 3′-position such as methoxy, ethoxy, allyloxy, isopropoxy, butoxy, isobutoxy, methoxyethyl, alkoxy, phenoxy, azido, amino, alkylamino, fluoro, chloro and bromo. Nucleosides and nucleotides include the natural D configurational isomer (D-form), as well as the L configurational isomer (L-form) (Beigelman, U.S. Pat. No. 6,251,666; Chu, U.S. Pat. No. 5,753,789; Shudo, EP0540742; Garbesi (1993) Nucl. Acids Res. 21:4159-65; Fujimori (1990) J. Amer. Chem. Soc. 112:7435; Urata, (1993) Nucleic Acids Symposium Ser. No. 29:69-70). When the nucleobase is purine, e.g., A or G, the ribose sugar is attached to the N9-position of the nucleobase. When the nucleobase is pyrimidine, e.g., C, T or U, the pentose sugar is attached to the N1-position of the nucleobase (Kornberg and Baker, (1992) DNA Replication, 2nd Ed., Freeman, San Francisco, Calif.).
One or more of the pentose carbons of a nucleoside may be substituted with a phosphate ester. In some embodiments, the phosphate ester is attached to the 3′- or 5′-carbon of the pentose. In some embodiments, the nucleosides are those in which the nucleotide base is a purine, a 7-deazapurine, a pyrimidine, a universal nucleotide base, a specific nucleotide base, or an analog thereof.
The term “nucleotide analog,” as used herein, refers to embodiments in which the pentose sugar and/or the nucleotide base and/or one or more of the phosphate esters of a nucleoside may be replaced with its respective analog. In some embodiments, exemplary pentose sugar analogs are those described above. In some embodiments, the nucleotide analogs have a nucleotide base analog as described above. In some embodiments, exemplary phosphate ester analogs include, but are not limited to, alkylphosphonates, methylphosphonates, phosphoramidates, phosphotriesters, phosphorothioates, phosphorodithioates, phosphoroselenoates, phosphorodiselenoates, phosphoroanilothioates, phosphoroanilidates, phosphoroamidates, boronophosphates, and may include associated counterions. Other nucleic acid analogs and bases include for example intercalating nucleic acids (INAs, as described in Christensen and Pedersen, 2002), and AEGIS bases (Eragen, U.S. Pat. No. 5,432,272). Additional descriptions of various nucleic acid analogs can also be found for example in (Beaucage et al., Tetrahedron 49(10):1925 (1993) and references therein; Letsinger, J. Org. Chem. 35:3800 (1970); Sprinzl et al., Eur. J Biochem. 81:579 (1977); Letsinger et al., Nucl. Acids Res. 14:3487 (1986); Sawai et al., Chem. Lett. 805 (1984), Letsinger et al., J. Am. Chem. Soc. 110:4470 (1988); and Pauwels et al., ChemicaScripta 26:141 (1986)), phosphorothioate (Mag et al., Nucleic Acids Res. 19:1437 (1991); and U.S. Pat. No. 5,644,048. Other nucleic analogs comprise phosphorodithioates (Briu et al., J. Am. Chem. Soc. 111:2321 (1989)), O-methylphosphoroamidite linkages (see Eckstein, Oligonucleotides and Analogues: A Practical Approach, Oxford University Press), those with positive backbones (Denpcy et al., Proc. Natl. Acad. Sci. USA 92:6097 (1995); non-ionic backbones (U.S. Pat. Nos. 5,386,023; 5,386,023; 5,637,684; 5,602,240; 5,216,141; and 4,469,863; Kiedrowshi et al., Angew. Chem. Intl. Ed. English 30:423 (1991); Letsinger et al., J. Am. Chem. Soc. 110:4470 (1988); Letsinger et al., Nucleoside & Nucleotide 13:1597 (194): Chapters 2 and 3, ASC Symposium Series 580, “Carbohydrate Modifications in Antisense Research,” Ed. Y. S. Sanghui and P. Dan Cook; Mesmaeker et al., Bioorganic & Medicinal Chem. Lett. 4:395 (1994); Jeffs et al., J. Biomolecular NMR 34:17 (1994); Tetrahedron Lett. 37:743 (1996)) and non-ribose backbones, including those described in U.S. Pat. Nos. 5,235,033 and 5,034,506, and Chapters 6 and 7, ASC Symposium Series 580, “Carbohydrate Modifications in Antisense Research,” Ed. Y. S. Sanghui and P. Dan Cook. Nucleic acids containing one or more carbocyclic sugars are also included within the definition of nucleic acids (see Jenkins et al., Chem. Soc. Rev. (1995), pp. 169-176). Several nucleic acid analogs are also described in Rawls, C & E News, Jun. 2, 1997, page 35.
The term “universal nucleotide base” or “universal base,” as used herein, refers to an aromatic ring moiety, which may or may not contain nitrogen atoms. In some embodiments, a universal base may be covalently attached to the C-1′ carbon of a pentose sugar to make a universal nucleotide. In some embodiments, a universal nucleotide base does not hydrogen bond specifically with another nucleotide base. In some embodiments, a universal nucleotide base hydrogen bonds with nucleotide base, up to and including all nucleotide bases in a particular target polynucleotide. In some embodiments, a nucleotide base may interact with adjacent nucleotide bases on the same nucleic acid strand by hydrophobic stacking. Universal nucleotides include, but are not limited to, deoxy-7-azaindole triphosphate (d7AITP), deoxyisocarbostyril triphosphate (dICSTP), deoxypropynylisocarbostyril triphosphate (dPICSTP), deoxymethyl-7-azaindole triphosphate (dM7AITP), deoxyImPy triphosphate (dImPyTP), deoxyPP triphosphate (dPPTP), or deoxypropynyl-7-azaindole triphosphate (dP7AITP). Further examples of such universal bases can be found, inter alia, in Published U.S. application Ser. No. 10/290,672, and U.S. Pat. No. 6,433,134.
As used herein, the terms “polynucleotide” and “oligonucleotide” are used interchangeably and mean single-stranded and double-stranded polymers of nucleotide monomers, including 2′-deoxyribonucleotides (DNA) and ribonucleotides (RNA) linked by internucleotidephosphodiester bond linkages, e.g., 3′-5′ and 2′-5′, inverted linkages, e.g., 3′-3′ and 5′-5′, branched structures, or internucleotide analogs. Polynucleotides have associated counter ions, such as H+, NH4+, trialkylammonium, Mg2+, Na+, and the like. A polynucleotide may be composed entirely of deoxyribonucleotides, entirely of ribonucleotides, or chimeric compositions thereof. Polynucleotides may be comprised of internucleotide, nucleobase and/or sugar analogs. Polynucleotides typically range in size from a few monomeric units, e.g., 3-40 when they are more commonly frequently referred to in the art as oligonucleotides, to several thousands of monomeric nucleotide units. Unless denoted otherwise, whenever a polynucleotide sequence is represented, it will be understood that the nucleotides are in 5′ to 3′ order from left to right and that “A” denotes deoxyadenosine, “C” denotes deoxycytosine, “G” denotes deoxyguanosine, and “T” denotes thymidine, unless otherwise noted.
As used herein, “nucleobase” means those naturally occurring and those non-naturally occurring heterocyclic moieties commonly known to those who utilize nucleic acid technology or utilize peptide nucleic acid technology to thereby generate polymers that can sequence specifically bind to nucleic acids. Non-limiting examples of suitable nucleobases include: adenine, cytosine, guanine, thymine, uracil, 5-propynyl-uracil, 2-thio-5-propynyl-uracil, 5-methylcytosine, pseudoisocytosine, 2-thiouracil and 2-thiothymine, 2-aminopurine, N9-(2-amino-6-chloropurine), N9-(2,6-diaminopurine), hypoxanthine, N9-(7-deaza-guanine), N9-(7-deaza-8-aza-guanine) and N8-(7-deaza-8-aza-adenine). Other non-limiting examples of suitable nucleobase include those nucleobases illustrated in FIGS. 2(A) and 2(B) of Buchardt et al. (WO92/20702 or WO92/20703).
As used herein, “nucleobase sequence” means any segment, or aggregate of two or more segments (e.g., the aggregate nucleobase sequence of two or more oligomer blocks), of a polymer that comprises nucleobase-containing subunits. Non-limiting examples of suitable polymers or polymers segments include oligodeoxynucleotides (e.g., DNA), oligoribonucleotides (e.g., RNA), peptide nucleic acids (PNA), PNA chimeras, PNA combination oligomers, nucleic acid analogs and/or nucleic acid mimics.
As used herein, “polynucleobase strand” means a complete single polymer strand comprising nucleobase subunits. For example, a single nucleic acid strand of a double stranded nucleic acid is a polynucleobase strand.
As used herein, “nucleic acid” is a nucleobase sequence-containing polymer, or polymer segment, having a backbone formed from nucleotides, or analogs thereof.
Preferred nucleic acids are DNA and RNA.
As used herein, nucleic acids may also refer to “peptide nucleic acid” or “PNA” means any oligomer or polymer segment (e.g., block oligomer) comprising two or more PNA subunits (residues), but not nucleic acid subunits (or analogs thereof), including, but not limited to, any of the oligomer or polymer segments referred to or claimed as peptide nucleic acids in U.S. Pat. Nos. 5,539,082; 5,527,675; 5,623,049; 5,714,331; 5,718,262; 5,736,336; 5,773,571; 5,766,855; 5,786,461; 5,837,459; 5,891,625; 5,972,610; 5,986,053; and 6,107,470; each of which is herein incorporated by reference. The term “peptide nucleic acid” or “PNA” shall also apply to any oligomer or polymer segment comprising two or more subunits of those nucleic acid mimics described in the following publications: Lagriffoul et al., Bioorganic & Medicinal Chemistry Letters, 4:1081-1082 (1994); Petersen et al., Bioorganic & Medicinal Chemistry Letters 6:793-796 (1996); Diderichsen et al., Tett. Lett. 37:475-478 (1996); Fujii et al., Bioorg. Med. Chem. Lett. 7:637-627 (1997); Jordan et al., Bioorg. Med. Chem. Lett. 7:687-690 (1997); Krotz et al., Tett. Lett. 36:6941-6944 (1995); Lagriffoul et al., Bioorg. Med. Chem. Lett. 4:1081-1082 (1994); Diederichsen, U., Bioorganic & Medicinal Chemistry Letters 7:1743-1746 (1997); Lowe et al., J. Chem. Soc. Perkin Trans. 1, (1997) 1:539-546; Lowe et al., J. Chem. Soc. Perkin Trans. 11:547-554 (1997); Lowe et al., J. Chem. Soc. Perkin Trans. 11:555-560 (1997); Howarth et al., J. Org. Chem. 62:5441-5450 (1997); Altmann, K.-H., et al., Bioorganic & Medicinal Chemistry Letters 7:1119-1122 (1997); Diederichsen, U., Bioorganic & Med. Chem. Lett. 8:165-168 (1998); Diederichsen et al., Angew. Chem. Int. Ed. 37:302-305 (1998); Cantin et al., Tett. Lett. 38:4211-4214 (1997); Ciapetti et al., Tetrahedron 53:1167-1176 (1997); Lagriffoule et al., Chem. Eur. J. 3:912-919 (1997); Kumar et al., Organic Letters 3(9):1269-1272 (2001); and the Peptide-Based Nucleic Acid Mimics (PENAMS) of Shah et al. as disclosed in WO96/04000.
The lipid nanoparticle of the invention differs from other similarly constituted materials by its morphology and characterized as having a substantially solid core. A lipid nanoparticle having a substantially solid core is a particle that does not have extended aqueous regions on the interior and that has an interior that is primarily lipid. In one embodiment, an extended region is a continuous aqueous region with a volume greater than half the particle volume. In a second embodiment, an extended aqueous region is more than 25% of the particle volume. The extent of internal aqueous regions may be determined by electron microscopy and appear as regions of low electron density. Further, because the interior of the solid core nanoparticle is primarily lipid, the aqueous content of the particle (the “trapped volume”) per lipid constituting the particle is less than that expected for a unilamellar bilayer lipid vesicle with the same radius. In one embodiment, the trapped volume is less than 50% of that expected for a unilamellar bilayer vesicle with the same radius. In a second embodiment, the trapped volume is less than 25% of that expected for a unilamellar bilayer vesicle of the same size. In a third embodiment, the trapped volume is less than 20% of the total volume of the particle. In one embodiment, the trapped volume per lipid is less than 2 microliter per micromole lipid. In another embodiment the trapped volume is less than 1 microliter per micromole lipid. In addition, while the trapped volume per lipid increases substantially for a bilayer lipid vesicle as the radius of the vesicle is increased, the trapped volume per lipid does not increase substantially as the radius of solid core nanoparticles is increased. In one embodiment, the trapped volume per lipid increases by less than 50% as the mean size is increased from a diameter of 20 nm to a diameter of 100 nm. In a second embodiment, the trapped volume per lipid increases by less than 25% as the mean size is increased from a diameter of 20 nm to a diameter of 100 nm. The trapped volume can be measured employing a variety of techniques described in the literature. Because solid core systems contain lipid inside the particle, the total number of particles of a given radius generated per mole of lipid is less than expected for bilayer vesicle systems. The number of particles generated per mol of lipid can be measured by fluorescence techniques amongst others.
The lipid nanoparticles of the invention can also be characterized by electron microscopy. The particles of the invention having a substantially solid core have an electron dense core as seen by electron microscopy. Electron dense is defined such that area-averaged electron density of the interior 50% of the projected area of a solid core particle (as seen in a 2-D cryo EM image) is not less than x % (x=20%, 40%, 60%) of the maximum electron density at the periphery of the particle. Electron density is calculated as the absolute value of the difference in image intensity of the region of interest from the background intensity in a region containing no nanoparticle.
Encapsulation Efficiency
The lipid nanoparticles of the invention can be further distinguished by the encapsulation efficiency. As described below, the lipid nanoparticles of the invention are prepared by a process by which nearly 100% (e.g., 80-100%) of the nucleic acid used in the formation process is encapsulated in the particles. In one embodiment, the lipid nanoparticles are prepared by a process by which from about 90 to about 95% of the nucleic acid used in the formation process is encapsulated in the particles.
Microfluidic Methods for Making Lipid Nanoparticles
In one aspect, the invention provides a method for making lipid nanoparticles containing an anionicmacromolecule using the lipid transfection reagent composition. In one embodiment, the method includes:
(a) introducing a first stream comprising an anionic macromolecules (e.g., polynucleic acid) in a first solvent into a microchannel; wherein the microchannel has a first region adapted for flowing one or more streams introduced into the microchannel and a second region for mixing the contents of the one or more streams;
(b) introducing a second stream comprising transfection reagent composition in a second solvent in the microchannel to provide first and second streams flowing in the device, wherein the transfection reagent composition comprises an ionizable cationic lipid, a neutral lipid, a sterol and a surfactant and wherein the first and second solvents are not the same;
(c) flowing the one or more first streams and the one or more second streams from the first region of the microchannel into the second region of the microchannel; and (d) mixing of the contents of the one or more first streams and the one or more second streams flowing in the second region of the microchannel to provide a third stream comprising lipid nanoparticles with encapsulated anionic macromolecules.
The contents of the first and second streams can be mixed by chaotic advection. In one embodiment, mixing the contents of the one or more first streams and the one or more second streams comprises varying the concentration or relative mixing rates of the one or more first streams and the one or more second streams. In the above embodiment, unlike known methods, the method does not include a dilution after mixing.
To further stabilize the third stream containing the lipid nanoparticles with encapsulated anionic macromolecules, the method can, but need not further include, comprising diluting the third stream with an aqueous buffer. In one embodiment, diluting the third stream includes flowing the third stream and an aqueous buffer into a second mixing structure. In another embodiment, the aqueous buffer comprising lipid nanoparticles with encapsulated anionic macromolecules is dialyzed to reduce the amount of the second solvent.
The first stream includes anionic macromolecules in a first solvent. Suitable first solvents include solvents in which the anionic macromolecules are soluble and that are miscible with the second solvent. Suitable first solvents include aqueous buffers. Representative first solvents include citrate and acetate buffers.
The second stream includes transfection reagent composition in a second solvent. Suitable second solvents include solvents in which the lipids and surfactants are soluble and that are miscible with the first solvent. Suitable second solvents include 1,4-dioxane, tetrahydrofuran, acetone, acetonitrile, dimethyl sulfoxide, dimethylformamide, acids, and alcohols. Representative second solvents include aqueous ethanol 90%.
The methods of the invention are distinguished from other microfluidic mixing methods in several ways. Whereas certain known methods require an equal or substantially equal proportion of aqueous and organic solvents (i.e., 1:1), the method of the invention generally utilizes a solvent ratio of aqueous to organic that exceeds 1:1. In certain embodiments, the solvent ratio of aqueous to organic is about 2:1. In certain embodiments, the solvent ratio of aqueous to organic is about 3:1. In certain embodiments, the solvent ratio of aqueous to organic is about 4:1. In certain other embodiments, the solvent ratio of aqueous to organic is about 5:1, about 10:1, about 50:1, about 100:1, or greater.
The lipid nanoparticles of the invention are advantageously formed in a microfluidic process that utilizes relatively rapid mixing and high flow rates. The rapid mixing provides lipid nanoparticles having the advantageous properties noted above including size, homogeneity, encapsulation efficiency. Mixing rates used in the practice of the method of the invention range from about 100 μsec to about 10 msec. Representative mixing rates include from about 1 to about 5 msec. Whereas hydrodynamic flow focusing methods operate at relatively low flow rates (e.g., 5 to 100 μL/minute) with relatively low lipid volumes, the method of the invention operates at relatively high flow rates and relatively high lipid volumes. In certain embodiments, for methods that incorporate a single mixing region (i.e., mixer), the flow rate is about 10 mL/min. For methods of the invention that utilize mixer arrays (e.g., 10 mixers), flow rates of 100 mL/minute are employed (for 100 mixers, flow rate 1000 mL/min). Thus, the methods of the invention can be readily scaled to provide quantities of lipid nanoparticles necessary for demanding production requirements. Coupled with the advantageous particle size and homogeneity and encapsulation efficiencies realized, the method of the invention overcomes disadvantages of known microfluidic methods for producing the lipid nanoparticles. One advantage of the methods of the invention for making the lipid nanoparticles is that the methods are scalable, which means that the methods do not change on scaling and that there is excellent correspondence on scaling.
Microfluidic Devices for Making Lipid Nanoparticles
In another aspect, the invention provides devices for producing a lipid nanoparticle encapsulating an anionic macromolecule using the transfection reagent composition. In one embodiment the device includes:
(a) a first inlet for receiving a first solution comprising a nucleic acid in a first solvent;
(b) a first inlet microchannel in fluid communication with the first inlet to provide a first stream comprising the nucleic acid in the first solvent;
(c) a second inlet for receiving a second solution comprising transfection reagent composition in a second solvent;
(d) a second inlet microchannel in fluid communication with the second inlet to provide a second stream comprising the transfection reagent composition in the second solvent; and
(e) a third microchannel for receiving the first and second streams, wherein the third microchannel has a first region adapted for flowing the first and second streams introduced into the microchannel and a second region adapted for mixing the contents of the first and second streams to provide a third stream comprising lipid nanoparticles with encapsulated nucleic acid.
In one embodiment, the device further includes means for diluting the third stream to provide a diluted stream comprising stabilized lipid nanoparticles with encapsulated anionic macromolecules.
The device of the invention is a microfluidic device including one or more microchannels (i.e., a channel having its greatest dimension less than 1 millimeter). In one embodiment, the microchannel has a hydrodynamic diameter from about 20 to about 300 μm. As noted above, the microchannel has two regions: a first region for receiving and flowing at least two streams (e.g., one or more first streams and one or more second streams) into the device. The contents of the first and second streams are mixed in the microchannel's second region. In one embodiment, the second region of the microchannel has a principal flow direction and one or more surfaces having at least one groove or protrusion defined therein, the groove or protrusion having an orientation that forms an angle with the principal direction (e.g., a staggered herringbone mixer), as described in U.S. Application Publication No. 2004/0262223, expressly incorporated herein by reference in its entirety. In one embodiment, the second region of the microchannel comprises bas-relief structures. To achieve maximal mixing rates, it is advantageous to avoid undue fluidic resistance prior to the mixing region. Thus, one embodiment of the invention is a device in which non-microfluidic channels, having dimensions greater than 1000 microns, are used to deliver the fluids to a single mixing channel.
In one embodiment the microfluidic device was produced by soft lithography, the replica molding of microfabricated masters in elastomer. The device has two inlets, one for each of the solutions prepared above, and one outlet. The microfluidic device was produced by soft lithography, the replica molding of microfabricated masters in elastomer. The device features a 300 μm wide and approximately 130 μm high mixing channel with herringbone structures formed by approximately 40 μm high and 75 m thick features on the roof of the channel. The device was sealed using an oxygen plasma treatment to a 40×36×2 mm glass slide with three 1.5 mm holes drilled to match the inlet and outlet ports of the device.
In a second embodiment, microfluidic devices are produced from a hard thermoplastic such as cyclic olefin copolymer. A negative tool was machined using a CNC mill and devices formed using injection molding. Channel dimensions were preserved with the addition of a draft angle ranging between 1° and 5° on vertical surfaces. Molded pieces were sealed to a blank substrate using a variety of techniques, including but not limited to: lamination, solvent welding, heat pressing and combinations thereof. Bonded devices were annealed to remove residual stresses from the production processes. Once formed, devices were installed and used in the custom instrument in the same way as elastomer devices.
In other aspects of the invention, the first and second streams are mixed with other micromixers. Suitable micromixers include droplet mixers, T-mixers, zigzag mixers, multilaminate mixers, or other active mixers.
Mixing of the first and second streams can also be accomplished with means for varying the concentration and relative flow rates of the first and second streams.
In another embodiment, the device for producing a lipid nanoparticle encapsulating a anionic macromolecule includes microchannel for receiving the first and second streams, wherein the microchannel has a first region adapted for flowing the first and second streams introduced into the microchannel and a second region adapted for mixing the contents of the first and second streams to provide a third stream comprising lipid nanoparticles with encapsulated anionic macromolecules. In this embodiment, the first and second streams are introduced into the microchannel by means other than first and second microchannels as noted above.
To achieve maximal mixing rates it is advantageous to avoid undue fluidic resistance prior to the mixing region. Thus one embodiment of the invention is a device in which non-microfluidic channels, having dimensions greater than 1000 microns, are used to deliver fluids to a single mixing channel. This device for producing a lipid nanoparticle encapsulating an anionic macromolecule includes:
(a) a single inlet microchannel for receiving both a first solution comprising an anionic macromolecule in a first solvent and a second solution comprising transfection reagent composition in a second solvent; and
(b) a second region adapted for mixing the contents of the first and second streams to provide a third stream comprising lipid nanoparticles with encapsulated anionic macromolecule.
In such an embodiment, the first and second streams are introduced into the microchannel by a single inlet or by one or two channels not having micro-dimensions, for example, a channel or channels having dimensions greater than 1000 μm (e.g., 1500 or 2000 μm or larger). These channels may be introduced to the inlet microchannel using adjacent or concentric macrosized channels.
Method for Delivering Anionic Macromolecules Using Lipid Nanoparticles
The transfection reagent composition of the present invention may be used to prepare lipid nanoparticles to deliver an anionic macromolecule to a cell, in vitro or in vivo. In particular embodiments, the anionic macromolecule is a nucleic acid, which is delivered to a cell using nucleic acid-lipid nanoparticles of the present invention. The methods and transfection reagent composition may be readily adapted for the delivery of any suitable anionic macromolecules for the treatment of any disease or disorder that would benefit from such treatment.
In certain embodiments, the present invention provides methods for introducing a nucleic acid into a cell. Preferred nucleic acids for introduction into cells are siRNA, miRNA, immune-stimulating oligonucleotides, plasmids, antisense and ribozymes. These methods may be carried out by contacting the lipid nanoparticles prepared with the transfection reagent composition of the present invention with the cells for a period of time sufficient for intracellular delivery to occur.
Typical applications include using well known procedures to provide intracellular delivery of siRNA to knock down or silence specific cellular targets. Alternatively applications include delivery of DNA or mRNA sequences that code for therapeutically useful polypeptides. In this manner, therapy is provided for genetic diseases by supplying deficient or absent gene products. Methods of the present invention may be practiced in vitro, ex vivo, or in vivo. For example, the compositions of the present invention can also be used for delivery of nucleic acids to cells in vivo, using methods which are known to those of skill in the art.
The delivery of siRNA by a lipid nanoparticle prepared using the transfection reagent composition of the invention and its effectiveness in silencing gene expression is described below.
For in vivo administration, the pharmaceutical compositions are preferably administered parenterally (e.g., intraarticularly, intravenously, intraperitoneally, subcutaneously, or intramuscularly). In particular embodiments, the pharmaceutical compositions are administered intravenously or intraperitoneally by a bolus injection. Other routes of administration include topical (skin, eyes, mucus membranes), oral, pulmonary, intranasal, sublingual, rectal, and vaginal.
In one embodiment, the present invention provides a method of modulating the expression of a target polynucleotide or polypeptide. These methods generally comprise contacting a cell with a lipid nanoparticle prepared using the transfection reagent of the present invention that is associated with a nucleic acid capable of modulating the expression of a target polynucleotide or polypeptide. As used herein, the term “modulating” refers to altering the expression of a target polynucleotide or polypeptide. Modulating can mean increasing or enhancing, or it can mean decreasing or reducing.
In related embodiments, the present invention provides a method of treating a disease or disorder characterized by overexpression of a polypeptide in a subject, comprising providing to the subject a pharmaceutical composition of the present invention, wherein the anionic macromolecule is selected from an siRNA, a microRNA, an antisense oligonucleotide, and a plasmid capable of expressing an siRNA, a microRNA, or an antisense oligonucleotide, and wherein the siRNA, microRNA, or antisense RNA comprises a polynucleotide that specifically binds to a polynucleotide that encodes the polypeptide, or a complement thereof.
In a further aspect, the invention provides a pharmaceutical composition comprising a lipid nanoparticle prepared using the transfection reagent of the invention and a pharmaceutically acceptable carrier or diluent. Representative pharmaceutically acceptable carriers or diluents include solutions for intravenous injection (e.g., saline or dextrose). The composition can take the form of a cream, ointment, gel, suspension, or emulsion.
The following is a description of a representative transfection reagent composition, lipid nanoparticle system, device and method for making the lipid nanoparticle system using the transfection reagent composition, and method for using a LNP for delivering anionic macromolecules.
Rapid Microfluidic Mixing Allows Production of Monodisperse Lipid Nanoparticles
Formulation of lipid nanoparticles was performed by rapidly mixing a lipid-ethanol solution with an aqueous buffer inside a microfluidic mixer (FIG. 5) designed to induce chaotic advection and provide a controlled mixing environment at intermediate Reynolds number (24<Re<240). The microfluidic channel contains herringbones that generate a chaotic flow by changing the orientation of herringbone structures between half cycles, causing a periodic change in the centers of local rotational and extensional flow.
The following representative transfection reagent composition include an ionizable cationic lipid, 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate (Cationic Lipid A) having an apparent pKa of 6.3 rendering the lipid suitable for encapsulation of siRNA at low pH and providing a near neutral cationic surface charge density at physiological pH. Using the transfection reagent composition as a model system, the choice of surfactant and mol % of the stabilizer on LNP formation by microfluidic mixing was determined. The ethanol solution contained the transfection reagent composition. The aqueous buffer contained siRNA to yield a siRNA/total lipid ratio of 0.06 (wt/wt) and the formed siRNA-LNP was diluted directly into buffer to reduce ethanol content to approximately 22 vol %. siRNA-LNP particle size was dependent on choice of surfactant and the mol % surfactant present in the transfection reagent composition. Particle size decreased with increasing mol % of surfactant in the transfection reagent composition. Increasing the proportion of the surfactant polyoxyethylene (40) stearate in the transfection reagent composition from 1 mol % to 10 mol % decreased resultant siRNA-LNP particle diameter from 103.2 nm to 37.4 nm (Table 1).
Self-Assembly in a Microfluidic Device can Produce LNP with Near Complete Encapsulation
In producing siRNA-LNP systems from transfection reagent composition, a robust process necessarily will provide high percent encapsulation of the OGN product. siRNA encapsulation was evaluated as a function of choice of surfactant and the relevant proportion of the surfactant in the transfection reagent composition. siRNA-LNP formulations achieved percent encapsulation approaching 100 percent independent of surfactant used and relative proportion of surfactant (Table 2).
siRNA-LNP Systems Produced by Microfluidics Using Transfection Reagent Composition can be Highly Potent Gene Silencing Agents In Vivo
The ability of siRNA-LNP systems to induce gene silencing in vivo following i.v. injection was investigated using the mouse Factor VII model. Formulations 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl 4-(dimethylamino)butanoate:DSPC:Cholesterol:Surfactant (50:10:40-% Surfactant:% Surfactant) with a siRNA-to-lipid ratio was 0.06 wt/wt were created using the microfluidic approach. Mice (n=3) were injected via the tail vein with a single dose equivalent to 1 mg/kg siRNA. Blood collection was performed 24 hrs post-injection and FVII levels were determined by colorimetric assay. The data (FIG. 1) indicates that FVII levels in the blood were reduced by >95% compared to control 24 hours after a single intravenous injection equivalent to siRNA dose of 1 mg/kg.
The results demonstrate that a microfluidic device containing a staggered herringbone mixer can be used to generate LNP using transfection reagent compositions varying in lipid compositions, can be used to efficiently encapsulate OGN such as siRNA and that the siRNA-LNPsystems produced exhibit excellent gene silencing capabilities both in vitro and in vivo.
The microfluidics device and system of the invention allow for use of the transfection reagent composition to form LNP, and to form LNP containing OGN of 100 nm size or smaller and provide OGN encapsulation 100%. With regard to formation of LNP, the rate and ratio of mixing are clearly the important parameters. Rapid mixing of the ethanol-lipid solution with aqueous buffer results in an increased polarity of the medium that reduces the solubility of dissolved lipids, causing them to precipitate out of solution and form nanoparticles. Rapid mixing causes the solution to quickly achieve a state of high supersaturation of lipid unimers throughout the entire mixing volume, resulting in the rapid and homogeneous nucleation of nanoparticles. Increased nucleation and growth of nanoparticles depletes the surrounding liquid of free lipid, thereby limiting subsequent growth by the aggregation of free lipid.
Solid Core LNP
LNP structures exhibit limit sizes indicating that ionizable cationic lipid forms inverted micellar structures in the LNP interior. The contribution of the cationic lipid to the electron dense LNP core raises the question of what the molecular structure of such LNP systems may be. It is logical to propose that the cationic lipid, in association with a counter-ion, adopts an inverted structure such as an inverted micelle, consistent with the propensity of these lipids for inverted structures such as the hexagonal H_IIphase in compositions with anionic lipids. In turn, this would suggest that LNP systems composed of pure cationic lipid should exhibit limit sizes with diameters in the range of 10 nm, which is essentially the thickness of two bilayers surrounding an inverted micelle interior with diameter 2-3 nm. The diameter of the aqueous channels found for phosphatidylethanolamine in the H_IIphase is 2.6 nm. The microfluidics formulation process provides fast mixing kinetics that drive the generation of limit size systems for LNP systems.
The model provides an understanding of how siRNA encapsulation efficiencies approaching 100% can be achieved during the microfluidic mixing formulation process. This is a major problem for siRNA encapsulation in bilayer systems because, assuming the cationic lipid is equally distributed on both sides of the bilayer, a maximum of 50% siRNA internalization would be expected. The model points to ways in which siRNA-LNP size, composition, and surface charge may be readily modulated. With regard to size, the limit size structure is clearly one that contains one siRNA monomer per particle, suggesting a limit size of approximately 15-20 nm. Such siRNA-LNP particles are readily achieved using microfluidic method of the invention. The limit size siRNA-LNP system consisting of a monomer of siRNA can be potentially used as a building block to achieve siRNA-LNP systems of varying composition and surface charge using microfluidic mixing technology. Rapid mixing of preformed limit size siRNA-LNP with an ethanol solution containing negatively charged lipids, for example, may be expected to result in an interaction with excess cationic lipids to produce internal inverted micellar core structures and a negatively charged surface.
The transfection reagent compositions and lipid nanoparticles of the invention described herein include (i.e., comprise) the components recited. In certain embodiments, the transfection reagent compositions and the lipid nanoparticles of the invention include the recited components and other additional components that do not affect the characteristics of the particles (i.e., the transfection reagent compositions and the lipid nanoparticles consist essentially of the recited components). Additional components that affect the transfection reagent compositions and the lipid nanoparticles' characteristics include components such as additional anionic macromolecules that disadvantageously alter or affect therapeutic profile and efficacy of the particles, additional components that disadvantageously alter or affect the ability of the particles to solubilize the recited anionic macromolecules components, and additional components that disadvantageously alter or affect the ability of the particles to increase the cellular uptake or bioavailability of the recited anionic macromolecules components. In other embodiments, the transfection reagent compositions and the lipid nanoparticles of the invention include only (i.e., consist of) the recited components.
In another aspect, the invention provides kits for preparing lipid nanoparticles. The kits include the transfection reagent composition of the invention. In certain embodiments, the kits include an anionic macromolecule (e.g., nucleic acid). The kits optionally include a device (e.g., microfluidic mixer) for making lipid nanoparticles.
Useful devices for use in the kit include devices described above and those described in WO 2011/140627 and WO 2013/059922, each expressly incorporated herein by reference in its entirety.
In certain embodiments, the device useful in the kit is a device for producing particles at small volumes. As used herein, the term “small volume” refers to volumes less than 2 mL and, in certain embodiments, volumes less than 1 mL (e.g., tens of microliters).
In one embodiment, the device includes:
(a) a first well for receiving a first solution comprising a first solvent;
(b) a first channel in fluid communication with the first well;
(c) a second well for receiving a second solution comprising a second solvent;
(d) a second channel in fluid communication with the second well;
(e) a third channel for receiving first and second streams flowed from the first and second wells through the first and second channels, respectively, wherein the third channel has a first region adapted for flowing the first and second streams introduced into the channel and a second region adapted for mixing the contents of the first and second streams to provide a third stream comprising particles; and
(f) a third well for receiving the third stream comprising particles.
This embodiment is illustrated in FIGS. 8, 9, and 12.
The device can include one or more first wells, one or more first channels, one or more second wells, one or more second channels, one or more third channels, and one or more third wells.
In one embodiment, the device further includes means for diluting the third stream to provide a diluted stream comprising stabilized particles.
In another embodiment, the device includes:
(a) a first well for receiving a first solution comprising a first solvent;
(b) a first channel in fluid communication with the first well; and
(c) a second well for receiving a second solution comprising a second solvent, wherein the second well further receives a first stream flowed from the first well through the first channel, and wherein the second well is adapted for mixing the contents of the first stream and second solution in the second well to provide a third solution comprising particles.
This embodiment is illustrated in FIGS. 10 and 11.
The device can include one or more first wells, one or more first channels, and one or more second wells.
In certain embodiments, the devices are macrofluidic or microfluidic devices. In certain embodiments, the first and second streams can be mixed by chaotic advection, turbulent mixing, jetting, vortex methods, bubble mixing, micro acoustic streaming, stirring, or other mixing methods. Mixing may be achieved by an active mixing device or passive mixing device. The mixing may occur in a continuous flow format or in defined volume format. The mixing may be achieved using a microfluidic mixer, including a herringbone mixer, zig-zag mixer, micro-jet mixer, or micro-vortex mixer. The mixing may be achieved using a macroscopic mixer, including a T-mixer, Y-mixer, or W-mixer.
In certain embodiments, the device is a microfluidic device including one or more microchannels (i.e., a channel having its greatest dimension less than 1 millimeter). In one embodiment, the microchannel has a hydrodynamic diameter from about 20 to about 400 μm. In certain embodiments, the microchannel has two regions: a first region for receiving and flowing at least two streams (e.g., one or more first streams and one or more second streams) into the device. The contents of the first and second streams are mixed in the microchannel's second region. In one embodiment, the second region of the microchannel has a principal flow direction and one or more surfaces having at least one groove or protrusion defined therein, the groove or protrusion having an orientation that forms an angle with the principal direction (e.g., a staggered herringbone mixer), as described in U.S. Patent Application Publication No. 2004/0262223, expressly incorporated herein by reference in its entirety. In one embodiment, the second region of the microchannel comprises bas-relief structures. To achieve maximal mixing rates, it is advantageous to avoid undue fluidic resistance prior to the mixing region. Thus, one embodiment of the invention is a device in which non-microfluidic channels, having dimensions greater than 1000 microns, are used to deliver the fluids to a single mixing channel.
In certain embodiments mixing of the first and second streams can also be accomplished with means for varying the concentration and relative flow rates of the first and second streams. Differing flow rations may be enabled by either differential pressure applied to the flows, differential pressure drops across the flow channels, differential channel impedances, or combination therein, applied to the first and second streams. Differential impedances of the channels through varying the channel heights, widths, lengths, or surface properties, may be used to achieve different flow rates. Fluidic surface tensions, viscosities, and other surface properties of the flows in the one or more first streams and the one or more second streams may be used or considered to achieve different flow rates.
In certain embodiments, the device further includes means for complete or partial purging of the system to minimize the waste volume. After or during manufacture of particles, the device is able to be flown into the one or more first streams and the one or more second streams from the first region of the channel into the second region of the channel a fluid or gas to expel the first stream and second streams. The first and second channel may be fully purged or partially purged under this method. Gasses such as air, nitrogen, argon or others may be used. Liquids including water, aqueous buffer, ethanol, oils, or any other liquid may be used.
In certain embodiments, the device enables backpressures to be applied to ensure the flows of the one or more first streams and the one or more second streams from the first region of the channel into the second region is limited until an initial desired input pressure is achieved. This may be achieved by applying pressure to the outlet channels, negative pressures to the input channels. This may be achieved by loading an outlet reservoir with fluid that may or may not be required in the final particle solution.
In certain embodiments, the device is designed such that fluids are introduced into the device in ways that minimize fluidic waste. This may be achieved by pipetting fluids into the device, pipetting fluids out of the device, connecting the device to syringes, or other methods.
In certain embodiments, the device is microfluidic and produced by soft lithography, the replica molding of microfabricated masters in elastomer. The device has two inlets, one for each of the solutions prepared above, and one outlet. The microfluidic device was produced by soft lithography, the replica molding of microfabricated masters in elastomer. In one example, the device features are 200 μm wide and approximately 70 μm high mixing channel with herringbone structures formed by approximately 25 μm high and 50 μm thick features on the roof of the channel. The device was sealed using an oxygen plasma treatment to a 75×25×1.5 mm glass slide. Other examples, include devices with widths and associated relative dimensions that are smaller (120 μm wide) or larger (300 μm wide). Input and output ports are drilled into the device.
In other embodiments, the device is microfluidic and produced from a hard thermoplastic such as cyclic olefin copolymer. A negative tool is machined using a CNC mill and devices formed using injection molding. Channel dimensions are preserved with the addition of a draft angle ranging between 1° and 5° on vertical surfaces. Molded pieces are sealed to a blank substrate using a variety of techniques, including but not limited to: lamination, solvent welding, heat pressing and combinations thereof. Bonded devices are annealed to remove residual stresses from the production processes. Once formed, devices are installed and used in the custom instrument in the same way as elastomer devices.
To achieve maximal mixing rates it is advantageous to avoid undue fluidic resistance prior to the mixing region. Thus one embodiment the device has non-microfluidic channels, having dimensions greater than 1000 microns, which are used to deliver fluids to a single mixing channel. This device for producing particles includes:
(a) a single inlet channel for receiving a first solution comprising solvent and none or some solution and a second solution comprising particle components in a second solvent; and
(b) a second region adapted for mixing the contents of the first and second streams to provide a third stream comprising particles.
In such an embodiment, the first and second streams are introduced into the channel by a single inlet or by one or two channels not having micro-dimensions, for example, a channel or channels having dimensions greater than 1000 μm (e.g., 1500 or 2000 μm or larger). These channels may be introduced to the inlet channel using adjacent or concentric macrosized channels.
The following examples are provided for the purpose of illustrating, not limiting, the claimed invention.

EXAMPLES

Materials

1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC) and cholesterol were obtained from Avanti Polar Lipids (Alabaster, Ala.). 4-(2-Hydroxyethyl)piperazine-1-ethanesulfonic acid (HEPES), cholesterol and surfactants were obtained from Sigma (St. Louis, Mo.). (Fair Lawn, N.J.). RNase A was obtained from Applied Biosystems/Ambion (Austin, Tex.). Factor VII (FVII) targeting, and low GC negative control siRNA were purchased from Invitrogen (Carlsbad, Calif.). Factor VII siRNA: 5′-GGAUCAUCUCAAGUCUUACTT-3′ [SEQ ID NO: 1] (FVII sense), and 5′-GUAAGACUUGAGAUGAUCCTT-3′ [SEQ ID NO: 2] (FVII antisense). 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate was synthesized by AlCana Technologies Inc. (Vancouver, BC).

Example 1

Preparation of LNP Systems

In the example, the preparation of an siRNA-LNP system using the preformed vesicle method is described.
siRNA-LNP systems were made using the preformed vesicle method as described in N. Maurer, K. F. Wong, H. Stark, L. Louie, D. McIntosh, T. Wong, P. Scherrer, S. Semple and P. R. Cullis, “Spontaneous Entrapment of Polynucleotides Upon Electrostatic Interaction With Ethanol Destabilized Cationic Liposomes: Formation of Small Multilamellar Liposomes,” Biophys. J. 80:2310-2326 (2001). Cationic lipid, DSPC, cholesterol and PEG-lipid were first solubilized in ethanol at the appropriate molar ratio. The lipid composition was then added dropwise to an aqueous buffer (citrate or acetate buffer, pH 4) while vortexing to a final ethanol and lipid concentration of 30% (v/v). The hydrated lipids were then extruded five times through two stacked 80 nm pore-sized filters (Nuclepore) at room temperature using a Lipex Extruder (Northern Lipids, Vancouver, Canada). The siRNA (solubilized in an identical aqueous solution containing 30% ethanol) was added to the vesicle suspension while mixing. A target siRNA/lipid ratio of 0.06 (wt/wt) was generally used. This composition was incubated for 30 minutes at 35° C. to allow vesicle re-organization and encapsulation of the siRNA. The ethanol was then removed and the external buffer replaced with phosphate-buffered saline (PBS) by dialysis (12-14 k MW cut-off, Spectrum medical instruments) to 50 mM citrate buffer, pH 4.0 and then dialysis to PBS, pH 7.4.

Example 2

Preparation of LNP Systems

In the example, a representative transfection reagent composition used to prepare a siRNA-LNP system of the invention using a microfluidic staggered herringbone mixer is described.
siRNA-LNP Preparation
Oligonucleotide (siRNA) solution was prepared in 25 mM acetate buffer at pH 4.0. Depending on the desired oligonucleotide-to-lipid ratio and formulation concentration, solutions were prepared at a target concentration of 0.3 mg/ml to 1.9 mg/ml total lipid. A lipid solution containing 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl 4-(dimethylamino)butanoate, DSPC, cholesterol, and a surfactant at the appropriate molar ratio was prepared in ethanol and diluted with 25 mM acetate buffer to achieve an ethanol concentration of 90% (v/v). FIG. 5 is a schematic illustration of the microfluidic apparatus used in this example. The device has two inlets, one for each of the solutions prepared above, and one outlet. The microfluidic device was produced by soft lithography, the replica molding of microfabricated masters in elastomer. The device has two inlets, one for each of the solutions prepared above, and one outlet. The microfluidic device was produced by soft lithography, the replica molding of microfabricated masters in elastomer. The device features a 300 μm wide and approximately 130 μm high mixing channel with herringbone structures formed by approximately 40 82 m high and 75 μm thick features on the roof of the channel. The device was sealed using an oxygen plasma treatment to a 40×36×2 mm glass slide with three 1.5 mm holes drilled to match the inlet and outlet ports of the device. The bonded device was installed into a custom instrument, having a top plate with o-rings to seal the device to the instrument, and a back plate with luer fitting for loading reagents in syringes. Once the device and reagents were loaded, the instrument acted as a syringe pump to dispense the fluid at the prescribed rate through the device. The flow rate of each stream was varied from 0.1 ml/min to 20 ml/min. The instrument introduces the two solutions into the microfluidic device, where they come into contact at a Y-junction. Insignificant mixing occurs under laminar flow by diffusion at this point, whereas the two solutions become mixed as they pass along the herringbone structures and around the serpentine channels.
Mixing occurs in these structures by chaotic advection, causing the characteristic separation of laminate streams to become increasingly small, thereby promoting rapid diffusion. This mixing occurs on a millisecond time scale and results in the lipids being transferred to a progressively more aqueous environment, reducing their solubility and resulting in the spontaneous formation of LNP. By including cationic lipids in the transfection reagent composition, entrapment of oligonucleotide species is obtained through association of the positively charged lipid head group and negatively charged oligonucleotide. Following mixing in the microfluidic device, the LNP composition was generally diluted into a glass vial containing two volumes of stirred buffer. Ethanol is finally removed through dialysis to 50 mM citrate buffer, pH 4.0 and then dialysis to PBS, pH 7.4. Empty vesicles were similarly produced, with the oligonucleotide absent from the buffer solution.
LNP Characterization
Particle size was determined by dynamic light scattering using a Nicomp model 370 Submicron Particle Sizer (Particle Sizing Systems, Santa Barbara, Calif.). Number-weighted and intensity-weighted distribution data was used. Lipid concentrations were verified by measuring total cholesterol using the Cholesterol E enzymatic assay from Wako Chemicals USA (Richmond, Va.). Removal of free siRNA was performed with VivaPureDMiniH columns (Sartorius Stedim Biotech GmbH, Goettingen, Germany). The eluents were then lysed in 75% ethanol and siRNA was quantified by measuring absorbance at 260 nm. Encapsulation efficiency was determined from the ratio of oligonucleotide before and after removal of free oligonucleotide content, normalized to lipid content.
In Vivo Activity of siRNA-LNP for FVII Activity
Six to eight week old, female C57Bl/6 mice were obtained from Charles River Laboratories. siRNA-LNP containing Factor VII siRNA were filtered through a 0.2 m filter and diluted to the required concentrations in sterile phosphate buffered saline prior to use. The formulations were administered intravenously via the lateral tail vein at a volume of 10 ml/kg. After 24 h, animals were anaesthetized with Ketamine/Xylazine and blood was collected by cardiac puncture. Samples were processed to serum (Microtainer Serum Separator Tubes; Becton Dickinson, N.J.) and tested immediately or stored at −70° C. for later analysis of serum Factor VII levels. All procedures were performed in accordance with local, state, and federal regulations as applicable and approved by the Institutional Animal Care and Use Committee (IACUC).
Serum Factor VII levels were determined using the colorimetric Biophen VII assay kit (Anaira). Control serum was pooled and serially diluted (200%-3.125%) to produce a calibration curve for calculation of FVII levels in treated animals. Appropriately diluted plasma samples from treated animals (n=3 per dosage) and a saline control group (n=4) were analyzed using the Biophen VII kit according to manufacturer's instructions. Analysis was performed in 96-well, flat bottom, non-binding polystyrene assay plates (Corning, Corning, N.Y.) and absorbance was measured at 405 nm. Factor VII levels in treated animals were determined from a calibration curve produced with the serially diluted control serum.

Example 3

Preparation and Characteristics of a Representative Lipid Nanoparticle using a Transfection Reagent Composition
In this example, a representative transfection reagent compositions of the invention, was used to prepare a representative siRNA-LNP of the invention is described.
The siRNA solution was prepared at 0.67 mg/mL in 25 mM acetate buffer, pH 4.0. The lipid solution was prepared to contain 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate:DSPC:cholesterol:SurfactantMryj 52 (50:10:37.5:2.5 mol %) at a concentration of 19.82 mg/mL in ethanol. The siRNA-to-lipid ratio was 0.07 (wt/wt). Each solution was input into the microfluidic mixer at a flow rate ratio of 3:1 aqueous:ethanol and a total flow rate of 12 mL/min resulting in a final ethanol concentration of 25 vol %. Ethanol was removed by dialysis with MES Citrate pH 6.7 (1:500 dilution). The final siRNA-LNP was prepared by further dialysis in phosphate-buffered saline (PBS) pH 7.4.
Particle size was determined by dynamic light scattering using a Malvern ZetasizerNanoZS (Malvern Instruments, Westborough, Mass., USA). Sample measurement was performed in PBS pH 7.4 and intensity-weighted distribution data was used. The particles had a mean particle diameter of 49.7 nm, with a polydispersity index (PDI)=0.06.
While illustrative embodiments have been illustrated and described, it will be appreciated that various changes can be made therein without departing from the spirit and scope of the invention.

Claims

1. A transfection reagent composition comprising:

(a) 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate, or a pharmaceutically acceptable salt thereof;

(b) 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC);

(c) cholesterol; and

(d) one or more surfactants selected from the group consisting of polyoxyethylene (20) oleyl ether, polyoxyethylene (23) lauryl ether, and polyoxyethylene (40) stearate.

2. The transfection reagent composition of claim 1, wherein the one or more surfactants is polyoxyethylene (20) oleyl ether.

3. The transfection reagent composition of claim 2, wherein a molar ratio of 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate:DSPC:cholesterol:polyoxyethylene (20) oleyl ether is 50:10:38:2.

4. The transfection reagent composition of claim 1, wherein the one or more surfactants is polyoxyethylene (23) lauryl ether.

5. The transfection reagent composition of claim 4, wherein a molar ratio of 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate:DSPC:cholesterol:polyoxyethylene (23) lauryl ether is 50:10:38:2.

6. The transfection reagent composition of claim 1, wherein the one or more surfactants is polyoxyethylene (40) stearate.

7. The transfection reagent composition of claim 6, wherein a molar ratio of 1,17-bis(2-octylcyclopropyl)heptadecan-9-yl-4-(dimethylamino)butanoate:DSPC:cholesterol:polyoxyethylene (40) stearate is 50:10:37.5:2.5.

8. A lipid nanoparticle comprising the transfection reagent composition of claim 1 and an anionic macromolecule.

9. The lipid nanoparticle of claim 8, wherein the lipid nanoparticle has a solid core.

10. The lipid nanoparticle of claim 8, wherein the anionic macromolecule is selected from the group consisting of nucleic acids, anionic proteins, and anionic peptides.

11. The lipid nanoparticle of claim 8, wherein the anionic macromolecule is a nucleic acid.

12. The lipid nanoparticle of claim 11, wherein the nucleic acid is a DNA, an RNA, a locked nucleic acid, a nucleic acid analog, or a plasmid capable of expressing a DNA or an RNA.

13. The lipid nanoparticle of claim 11, wherein the nucleic acid is an ssRNA, an siRNA, a microRNA, or an mRNA.

14. The lipid nanoparticle of claim 11, wherein the nucleic acid is an antisense oligonucleotide.

15. The lipid nanoparticle of claim 11, wherein the nucleic acid is a hybridization probe.

16. The lipid nanoparticle of claim 15, wherein the hybridization probe is a molecular beacon.