Patent Application
20140363378
Early detection and identification of a suspected tumor in a localized stage significantly improves the chances for successful treatment and elimination of the cancerous tissue. A large number of imaging strategies have therefore been designed, using a variety of techniques and modalities to aid the physician in making an accurate diagnosis as early as possible. Unfortunately, conventional imaging techniques such as computerized tomography (CT) and magnetic resonance imaging (MRI) are limited in their ability to afford a conclusive diagnosis of a suspected lesion, since they are only capable of observing differences in the density or morphology of tissues. A more invasive and costly biopsy procedure is often necessary to provide a definitive diagnosis. In contrast, nuclear medicine techniques such as positron emission tomography (PET) and single photon emission tomography (SPECT) can provide functional or biochemical information about a particular organ or area of interest. However, the success of these nuclear imaging techniques depends in large part on the selective uptake and detection of appropriate radiopharmaceuticals and on the spatial resolution of the imaging technique. Spatial resolution limits the sensitivity of SPECT and PET to lesions >1 cm in diameter. Selective uptake, in turn, depends upon the development of radiopharmaceuticals with a high degree of specificity for the target tissue. Tumor-localizing agents developed thus far for oncological use have had only limited application. In PET imaging, fluorodeoxyglucose (18F-FDG) is used for imaging tumors in oncology, where a static FDG PET scan is performed and the tumor FDG uptake is analyzed in terms of Standardized Uptake Value (SUV). 18F-FDG has had the widest application, despite some limitations in specificity and the aforementioned limitation in sensitivity. There is therefore a need in the art for imaging and therapeutic agents that accumulate in tumor tissue but exhibit a rapid clearance from non-target tissues, and also a need for such agents that can be imaged by higher spatial resolution imaging scanners like MRI and CT. Such agents could assist in the non-invasive imaging of primary tumors and metastases and could serve as carriers for cytotoxic agents for site-specific eradication of malignant tumor tissue or acidic inflamed tissue.
Disclosed are compositions transform into larger, bulky, more slowly diffusing materials upon reaching an acidic extracellular tissue environment, which will cause a higher relative concentration in the acidic environment for imaging, non radioactive drug delivery, or radiotherapeutic agents at the tissue site compared to the surrounding tissue or circulation. In particular, self-assembling molecules are disclosed that transform from isolated molecules or spherical micelles into cylindrical nanofibers in an acidic extracellular microenvironment (e.g., malignant tumor tissue or inflamed joints). This transition is rapid and reversible, indicating the system is in thermodynamic equilibrium. A composition is therefore disclosed that contains a plurality of biocompatible self-assembling molecules that are present as isolated molecules or spherical micelles in the neutral pH and isotonic conditions of blood serum and normal extracellular environment, and that transform into cylindrical nanofibers in an acidic extracellular environment. At least a portion of the plurality of biocompatible self-assembling molecules may be conjugated to a diagnostic or therapeutic agent such that self assembly of the molecules in the acidic environment of a tissue results in accumulation of the diagnostic or therapeutic agent in the tissue.
Disclosed is a composition that, upon reaching the acidic extracellular tumor environment, transforms into a bulky, more slowly diffusing material, which can be used to achieve a higher relative concentration of diagnostic or therapeutic drugs for imaging, non radioactive drug delivery, or radiotherapeutic agents at the tumor site compared to the bloodstream. In particular, disclosed are self-assembling molecules that transform from isolated molecules or spherical micelles into nanofibers in the acidic extracellular microenvironment of malignant tumor tissue or acidic inflamed tissues. This transition is rapid and reversible, indicating the system is in thermodynamic equilibrium.
The disclosed self-assembling molecules are able to circulate through the vasculature until they encounter an acidic environment. However, since kidneys can also contain an acidic microenvironment, the disclosed self-assembling molecules preferably do not pass through the glomerular basement membrane. Therefore, the self-assembling molecules may have a size and/or charge that reduces glomerular filtration. For example, the self-assembling molecules may have a molecular weight of at least 50 kD, 75 kD, or 100 kD.
In some cases, the self-assembling molecule is conjugated to a macromolecule or particle, such as serum albumin, a polymeric micelle, a liposome, or a polymeric nanoparticle (e.g., a biodegradable polymeric nanoparticle), which due its size and/or charge is excluded from the glomerular filtrate. In other embodiments, the self-assembling molecules are designed to form spherical micelles in blood serum that do not pass through the glomerular basement membrane. Typical micelle sizes are about 10 nm, and the range is from 5 nm to 100 nm.
A composition is therefore disclosed that contains a plurality of biocompatible self-assembling molecules that are isolated molecules or spherical micelles in the neutral pH and isotonic conditions of blood serum, and which transform into cylindrical nanofibers in the acidic extracellular environment of tumors. For example, the plurality of peptide amphiphiles can exist as spherical micelles when in a physiological environment having a pH of 7.30 to 7.45, and transform into cylindrical nanofibers when in a physiological environment having a pH less than 7.3, e.g., environments with a pH of about 5.1 to 7.3, or preferably about 6.4 to 7.3.
At least a portion of the plurality of biocompatible self-assembling molecules are conjugated to a diagnostic or therapeutic agent such that self assembly of the molecules in the acidic environment of a tumor results in accumulation of the diagnostic or therapeutic agent in the tumor.
Peptide Amphiphile
In some embodiments, the self-assembling molecule contains a peptide amphiphile (or petidomimetic thereof). Peptide amphiphiles are peptide-based molecules that self-assemble into high aspect ratio nanofibers. These molecules typically have three regions: a hydrophobic tail, a region of beta-sheet forming amino acids, and a peptide epitope designed to allow solubility of the molecule in water, perform a biological function by interacting with living systems, or both. Self-assembly occurs by the combination of hydrogen-bonding between beta-sheet forming amino acids and hydrophobic collapse of the tails to yield the formation of spherical micelles or cylindrical nanofibers that present the peptide epitope at extremely high density at the surface.
The term “peptide” refers to any peptide, oligopeptide, polypeptide, or protein. A peptide is comprised of consecutive amino acids. The term encompasses naturally occurring or synthetic amino acids. The term “peptide” includes amino acids joined to each other by peptide bonds or modified peptide bonds, e.g., peptide isosteres, and may contain modified amino acids other than the 20 gene-encoded amino acids. The peptide can be modified by either a natural process, such as post-translational processing, or by chemical modification techniques which are well known in the art. Modifications can occur anywhere in the polypeptide, including the peptide backbone, the amino acid side-chains and the amino or carboxyl termini. The same type of modification can be present in the same or varying degrees at several sites in a given polypeptide. Also, a given peptide can have many types of modifications. Modifications include, without limitation, acetylation, acylation, ADP-ribosylation, amidation, covalent cross-linking or cyclization, covalent attachment of flavin, covalent attachment of a heme moiety, covalent attachment of a nucleotide or nucleotide derivative, covalent attachment of a lipid or lipid derivative, covalent attachment of a phosphytidylinositol, disulfide bond formation, demethylation, formation of cysteine or pyroglutamate, formylation, gamma-carboxylation, glycosylation, GPI anchor formation, hydroxylation, iodination, methylation, myristolyation, oxidation, pegylation, proteolytic processing, phosphorylation, prenylation, racemization, selenoylation, sulfation, and transfer-RNA mediated addition of amino acids to protein such as arginylation.
The term “peptidomimetic” refers to a mimetic of a peptide which includes some alteration of the normal peptide chemistry. Peptidomimetics typically enhance some property of the original peptide, such as increase stability, increased efficacy, enhanced delivery, increased half life, etc. Methods of making peptidomimetics based upon a known polypeptide sequence is described, for example, in U.S. Pat. Nos. 5,631,280; 5,612,895; and 5,579,250. Use of peptidomimetics can involve the incorporation of a non-amino acid residue with non-amide linkages at a given position. Some non-limiting examples of unnatural amino acids which may be suitable amino acid mimics include β-alanine, L-α-amino butyric acid, L-γ-amino butyric acid, L-α-amino isobutyric acid, L-ε-amino caproic acid, 7-amino heptanoic acid, L-aspartic acid, L-glutamic acid, N-ε-Boc-N-α-CBZ-L-lysine, N-ε-Boc-N-α-Fmoc-L-lysine, L-methionine sulfone, L-norleucine, L-norvaline, N-α-Boc-N-δCBZ-L-ornithine, N-δ-Boc-N-α-CBZ-L-ornithine, Boc-p-nitro-L-phenylalanine, Boc-hydroxyproline, and Boc-L-thioproline.
Formation of Spherical Micelles and Cylindrical Nanofibers
As stated above, the disclosed self-assembling molecules in some embodiments form spherical micelles in the neutral pH and isotonic conditions of blood serum, and transform into cylindrical nanofibers in the acidic extracellular environment of tumors.
A “spherical micelle” is an aggregate of surfactant molecules (e.g., peptide amphiphiles) dispersed in a liquid. A typical micelle in aqueous solution forms an aggregate with the hydrophilic “head” regions in contact with surrounding solvent, sequestering the hydrophobic single-tail regions in the micelle centre. The shape and size of a micelle is a function of the molecular geometry of its surfactant molecules and solution conditions such as surfactant concentration, temperature, pH, and ionic strength.
Micelles only form when the concentration of surfactant is greater than the critical micelle concentration (CMC), and the temperature of the system is greater than the critical micelle temperature, or Krafft temperature. Micelles can form spontaneously because of a balance between entropy and enthalpy. In water, the hydrophobic effect is the driving force for micelle formation, despite the fact that assembling surfactant molecules together reduces their entropy. At very low concentrations of the lipid, only monomers are present in true solution. As the concentration of the lipid is increased, a point is reached at which the unfavorable entropy considerations, derived from the hydrophobic end of the molecule, become dominant. At this point, the lipid hydrocarbon chains of a portion of the lipids must be sequestered away from the water. Therefore, the lipid starts to form micelles. Broadly speaking, above the CMC, the entropic penalty of assembling the surfactant molecules is less than the entropic penalty of caging the surfactant monomers with water molecules. Also important are enthalpic considerations, such as the electrostatic interactions that occur between the charged parts of surfactants.
The spherical micelles are preferably of a size and charge which allows them to preferentially accumulate in the tumor by the enhanced permeability and retention (EPR), but not be rapidly removed from the bloodstream by glomerular filtration. The EPR effect is a consequence of the abnormal vasculature frequently associated with solid tumors. The vasculature of tumors is typically characterized by blood vessels containing poorly-aligned defective endothelial cells with wider than normal fenestrations. As a result, micelles having an average hydrodynamic diameter of from about 8 nm to about 25 nm can preferentially extravasate from the tumor vasculature, and accumulate within the solid tumor.
Therefore, when present in serum at diagnostically or therapeutically effective concentrations, the disclosed self-assembling molecules preferably form micelles with a hydrodynamic diameter of at least about 8 nm (e.g., at least about 10 nm, at least about 15 nm, at least about 20 nm). In some cases, when present in serum at diagnostically or therapeutically effective concentrations, the disclosed self-assembling molecules preferably form micelles with a hydrodynamic diameter no larger than about 25 nm (e.g., less than about 25 nm, less than about 20 nm, or less than about 15 nm). Dynamic Light Scattering can be used to determine the hydrodynamic diameter of the micelles.
When present in serum at diagnostically or therapeutically effective concentrations, the disclosed self-assembling molecules can form micelles with a hydrodynamic diameter ranging from any of the minimum to any of the maximum diameters described above. For example, the self-assembling molecules can form micelles with a hydrodynamic diameter ranging from about 8 nm to about 25 nm (e.g., from about 8 nm to about 20 nm, or from about 8 nm to about 15 nm).
The spherical micelles or isolated molecules (e.g., bound to a macromolecule) transform into cylindrical nanofibers in the acidic extracellular environment of tumors. The nanofibers are preferably of a size and shape to enhance accumulation within tumor tissue. For example, the cylindrical nanofibers can be greater than about 200 nm, 300 nm, 500 nm, 1000 nm, or 5000 nm in length. In addition, the length of the cylindrical nanofibers may be at least 10 times greater, 20 times greater, or 50 times greater than the diameter of the cylindrical nanofibers, i.e., a length:diameter aspect ratio greater than 10, 20, or 50.
Balance of Attractive and Repulsive Forces
In some embodiments, the self-assembling molecule has three main segments: a hydrophobic alkyl tail, a beta-sheet forming sequence, and a charged sequence. Decreasing the repulsive interaction of the charged region either via electrostatic screening, or by lowering the degree of side-chain ionization with pH, causes these molecules to form nanofibers. By balancing the attractive hydrophobic and hydrogen bonding forces, and repulsive electrostatic and steric forces, the self-assembly morphology and the transition pH can be systematically shifted by tenths of pH values. Moreover, inclusion of sterically bulky agents on the exterior periphery can affect this balance, e.g., by shifting self-assembly to more acidic pH values, and inducing a spherical micellar morphology at high pH and concentration ranges.
The disclosed self-assembling molecules may be designed in such a way that the attractive supramolecular forces (hydrophobic-hydrophobic interactions, beta-sheet formation) and the repulsive supramolecular forces (electrostatic repulsion, sterics) of the molecule are precisely balanced. For example, the repulsive forces can be increased by increasing the number of charged amino acid residues, or adding a unit with larger hydrophilicity or greater steric hindrance, such as a chelating agent. Increasing the attractive forces can be done by using longer alkyl chains, as well as increasing the number of beta-sheet forming residues
In some embodiments, the biocompatible self-assembling molecule is defined by Formula (I)
Cn—Z-A-X (I)
wherein
Cn represents an alkyl, alkenyl, or alkynyl group;
Z represents a conjugate comprising Bo, Up, Nq, and Y arranged any order, with the proviso that Bo is positioned between Nq and Cn;
A is absent, or represents a hydrophilic linking group; and
X represents a terminating residue.
Cn can be an alkyl, alkenyl, or alkynyl group. “Alkyl,” as used herein, refers to the radical of a saturated aliphatic group, including straight-chain alkyl and branched-chain alkyl groups. In some embodiments, the alkyl group comprises 30 or fewer carbon atoms in its backbone (e.g., C1-C30 for straight chain, C3-C30 for branched chain). For example, the alkyl group can comprise 25 or fewer carbon atoms, 22 or fewer carbon atoms, 20 or fewer carbon atoms, 19 or fewer carbon atoms, 18 or fewer carbon atoms, 17 or fewer carbon atoms, 16 or fewer carbon atoms, 15 or fewer carbon atoms, 14 or fewer carbon atoms, 12 or fewer carbon atoms, 12 or fewer carbon atoms, 10 or fewer carbon atoms, 8 or fewer carbon atoms, or 6 or fewer carbon atoms in its backbone. In some embodiments, the alkyl group can comprise 6 or more carbon atoms, 8 or more carbon atoms, 10 or more carbon atoms, 11 or more carbon atoms, 12 or more carbon atoms, 13 or more carbon atoms, 14 or more carbon atoms, 15 or more carbon atoms, 16 or more carbon atoms, 17 or more carbon atoms, 18 or more carbon atoms, 19 or more carbon atoms, or 20 or more carbon atoms in its backbone. The alkyl group can range in size from any of the minimum number of carbon atoms to any of the maximum number of carbon atoms described above. For example, the alkyl group can be a C6-C30 alkyl group (e.g., a C12-C22 alkyl group, or a C12-C18 alkyl group). The term alkyl includes both unsubstituted alkyls and substituted alkyls, the latter of which refers to alkyl groups having one or more substituents, such as a halogen or a hydroxy group, replacing a hydrogen on one or more carbons of the hydrocarbon backbone. The alkyl groups can also comprise between one and four heteroatoms (e.g., oxygen, nitrogen, sulfur, and combinations thereof) within the carbon backbone of the alkyl group. “Alkenyl” and “Alkynyl”, as used herein, refer to unsaturated aliphatic groups containing one or more double or triple bonds analogous in length (e.g., C2-C30) and possible substitution to the alkyl groups described above.
In certain embodiments, Cn is straight-chain C12-C18 alkyl group (e.g., a straight-chain C14-C16 alkyl group). For example, Cn can be a lauryl group, a myristyl group, a palmityl group, or a stearyl group.
B can be an amino acid with high beta-sheet propensity. Both natural and synthetic amino acids with high beta-sheet propensity are known in the art. Examples of amino acids with high beta-sheet propensity (B) include isoleucine, phenylalanine, valine, and tyrosine, as well as synthetic amino acids, including phenylglycine and napthyl alanine
U can be an uncharged amino acid with poor beta-sheet propensity. Both natural and synthetic uncharged amino acids with poor beta-sheet propensity are known in the art. Examples of uncharged amino acids with poor beta-sheet propensity (U) include threonine, tryptophan, leucine, methionine, glutamine, serine, alanine, asparagines, glycine, or L-homoglutamine.
N can be an anionic amino acid. Anionic amino acids can include amino acids (natural or synthetic) which are negatively charged under physiological conditions. In certain cases, N is an amino acid which comprises a side-chain comprising a carboxylic acid moiety. Examples of anionic amino acids include aspartic acid (D) glutamic acid (E), 4-fluoroglutamic acid, and beta-homo-glutamic acid.
Y can be a spacer group comprising a diagnostic or therapeutic agent. For example, Y can be derived from a divalent molecule comprising a side-chain which includes a therapeutic or diagnostic agent. In certain cases, Y comprises an amino acid having a therapeutic or diagnostic agent covalently attached to the amino acid side-chain.
For example, Y can be derived from an amino acid (natural or synthetic) comprising a side-chain which includes a functional group (e.g., an amine, a carboxylic acid, an aldehyde, an azide, an alkyne, a thiol, an epoxide, or an alcohol). A therapeutic or diagnostic agent (e.g., a chelating agent configured to coordinate a metal ion with diagnostic or therapeutic potential, an aromatic or alkyl entity that can be radiohalogenated) comprising a functional group can be covalently attached to the amino acid via reaction with the functional group in the amino acid side-chain. For example, Y can be lysine conjugated to DO3A.
The therapeutic or diagnostic agent can be directly connected to the amino acid side-chain. In these embodiments, the therapeutic or diagnostic agent comprises a functional group which is reacted with the functional group in the amino acid side-chain, forming a covalent bond between the agent and the amino acid.
In other embodiments, the therapeutic or diagnostic agent can be connected to the amino acid side-chain via a linker. A linker is a divalent chemical group that serves to couple the therapeutic or diagnostic agent to the amino acid side-chain while not adversely affecting either the activity of the agent or the self-assembly of the biocompatible self-assembling molecule. Suitable linking groups include peptides alone, non-peptide groups (e.g., alkyl, alkenyl, or alkynyl groups), or a combination thereof.
For example, the therapeutic or diagnostic agent can be connected to the amino acid side-chain via a linker which includes a C2-C12 alkyl group, a peptide (e.g., diglycine, triglycine, gly-gly-glu, gly-ser-gly, etc.) in which the total number of atoms in the peptide backbone is less than or equal to twelve, or combinations thereof. In one embodiment, the linker is derived from a substituted alkyl group defined by the formula R1—(CH2)n—R2, wherein n is an integer from 1-10 (e.g., an integer from 3 to 9), R1 represents a functional group that can be reacted with the functional group in the amino acid side-chain, and R2 represents a functional group that can form a covalent bond with the therapeutic or diagnostic agent.
In some embodiments, A absent, in which case Z is directly connected to X. In other embodiments, A is present, and represents a hydrophilic linking group. When the biocompatible self-assembling molecules form micelles in solution, A can be present on the surface of the micelles. In some cases, A is selected so as to provide micelles with prolonged in vivo residence time (e.g., by minimizing uptake of the micelless by the reticuloendothelial system (RES)). For example, A can be a hydrophilic oligomer or polymer segment, such as a hydrophilic oligo- or polyalkylene oxide (e.g., oligoethylene glycol or polyethylene glycol (PEG)).
A can be a hydrophilic oligo- or polyalkylene oxide having a molecular weight of less than about 5000 Da (e.g., less than 4500 Da, less than about 4000 Da, less than about 3500 Da, less than about 3000 Da, less than about 2500 Da, less than about 2000 Da, less than about 1500 Da, less than about 1000 Da, less than about 800 Da, less than about 750 Da, less than about 600 Da, less than about 500 Da, less than about 450 Da, less than about 400 Da, less than about 350 Da, less than about 300 Da, less than about 250 Da, less than about 200 Da, less than about 150 Da, or less than about 100 Da). A can be a hydrophilic oligo- or polyalkylene oxide having a molecular weight of greater than about 50 Da (e.g., greater than about 100 Da, greater than about 150 Da, greater than about 200 Da, greater than about 250 Da, greater than about 300 Da, greater than about 350 Da, greater than about 400 Da, greater than about 450 Da, greater than about 500 Da, greater than about 600 Da, greater than about 750 Da, greater than about 800 Da, greater than about 1000 Da, greater than about 1500 Da, greater than about 2000 Da, greater than about 2500 Da, greater than about 3000 Da, greater than about 3500 Da, greater than about 4000 Da, or greater than about 4500 Da).
A can be a hydrophilic oligo- or polyalkylene oxide having a molecular weight ranging from any of the minimum molecular weights to any of the maximum molecular weights described above. For example, A can be a hydrophilic oligo- or polyalkylene oxide having a molecular weight ranging from about 50 Da to about 5000 Da (e.g., from about 50 Da to about 1000 Da, from about 50 Da to about 500 Da, or from about 100 Da to about 500 Da).
In certain embodiments, A is a hydrophilic oligoalkylene oxide having a molecular weight of less than about 400 Da. For example, the oligoalkylene oxide can be oligoethylene oxide. In certain embodiments, A is defined by the following formula (—O—CH2—CH2—)r, where r is an integer ranging from 1 to 8.
X can be any terminating residue. For example, X can be a chemical moiety resulting from the cleavage of the biocompatible self-assembling molecule from a solid support resin used during solid phase peptide synthesis. For example, X can be an amine, an alcohol, an amide group, or a carboxylic acid group (e.g., the NH2 or COOH group of a C-terminal or N-terminal amino acid). Alternatively, the terminating residue X can be a propionic amide or propionic acid group. X can also be a chemically modified form of such a moiety (e.g., an alkylated amine or an esterified carboxylic acid).
Each of the integers (q, o, p, and n, where is an integer representing the number of carbon atoms in Cn) in Formula (I) can be proportionally increased so as to provide larger (i.e., higher molecular weight) self-assembled molecules which can have a similar balance of attractive and repulsive forces. For example, o can represents an integer from 2 to 4, p can represents an integer from 10 to 40, and q can represents an integer from 7 to 14, and n can range from 20 to 40 (e.g., Cn represents a C20-C40 alkyl group); or o can represents an integer from 4 to 6, p can represents an integer from 20 to 60, and q can represents an integer from 12 to 21, and n can range from 30 to 60 (e.g., Cn represents a C30-C60 alkyl group).
As described above, Z represents a linear conjugate comprising Bo, Up, Nq, and Y arranged any order, with the proviso that Bo is positioned between Nq and Cn. In some embodiments, Z can further include one or more additional Bo and/or Up segments. For example, Z can be a linear conjugate of Up, Bo, Up, Nq, and Y, or a linear conjugate of Bo, Up, Bo, Nq, and Y. The order of B to U does not strongly affect the transition. Likewise, the order of N to Y does not strongly affect the transition.
In some embodiments, the biocompatible self-assembling molecule is defined by one of the formulae below:
Cn—Bo—Up—Nq—Y-A-X (II),
Cn—Bo—Up—Y—Nq-A-X (III),
Cn—Up—Bo—Y—Nq-A-X (IV), or
Cn—Up—Bo—Nq—Y-A-X (V),
wherein Cn, B, o, U, p, Y, N, q, A, and X are defined as in Formula (I).
In some embodiments, the biocompatible self-assembling molecule is defined by one of the formulae below:
(Cn)—(BoUp)—(NqY)—(—O—CH2—CH2—)r-propionic amide (VI), or
(Cn)—(BoUp)—(NqY)—NH2 (VII),
wherein Cn, B, o, U, p, Y, N, and q are defined as in Formula (I), Y represents a lysine conjugated to a therapeutic or diagnostic agent (e.g., aDO3A chelating agent optionally bound to a trivalent metal ion), and r represents an integer from 0 to 8. In certain embodiments, the ratio of n:o:q (where n is an integer representing the number of carbon atoms in Cn) is 16-17:1:3-4 or 15-16:2:5-7.
In other embodiments, the biocompatible self-assembling molecule comprises the formula:
(Cn)—(BoUp)—(Nq-1Y)—(—O—CH2—CH2—)r-propionic acid (VIII), or
(Cn)—(BoUp)—(Nq-1Y)—COOH; (IX),
wherein Cn, B, o, U, p, Y, N, and q are defined as in Formula (I), Y represents a lysine conjugated to a therapeutic or diagnostic agent (e.g., aDO3A chelating agent optionally bound to a trivalent metal ion, or a halogenated aromatic or aliphatic), and r represents an integer from 0 to 8. In certain embodiments, the ratio of n:o:q (where n is an integer representing the number of carbon atoms in Cn) is 16-17:1:2-3 or 15-16:2:4-6.
Diagnostic and Therapeutic Agents
The disclosed self-assembling molecules contain diagnostic or therapeutic agents for detecting and/or treating tissue where the self-assembling molecules accumulate, e.g., malignant tumors or inflamed joints. The diagnostic or therapeutic agent can be any molecule suitable for molecular imaging or targeted tumor therapy, respectively. In some embodiments, the diagnostic agent is a molecule detectable in the body of a subject by an imaging technique such as X-ray radiography, ultrasound, computed tomography (CT), single-photon emission computed tomography (SPECT), magnetic resonance imaging (MRI), positron emission tomography (PET), Optical Fluorescent Imaging, Optical Visible light imaging, and nuclear medicine including Cerenkov Light Imaging. For example, the diagnostic agent can comprise a radionuclide, paramagnetic metal ion, or a fluorophore.
Metal Chelators
The terms “metal chelator” and “chelating agent” refer to a polydentate ligand that can form a coordination complex with a metal atom. It is generally preferred that the coordination complex is stable under physiological conditions. That is, the metal will remain complexed to the chelator in vivo.
In some cases, the metal chelator is a molecule that complexes to a radionuclide metal or paramagnetic metal ion to form a metal complex that is stable under physiological conditions. The metal chelator may be any of the metal chelators known in the art for complexing a medically useful paramagnetic metal ion, or radionuclide.
In some cases, such as in the case of self-assembling molecules designed for radiopharmaceutical or radiotherapy applications, it can be convenient to prepare the complexes comprising a radionuclide, at or near the site where they are to be used (e.g., in a hospital pharmacy or clinic). Accordingly, in some embodiments, the self-assembling molecule comprises a metal chelator uncomplexed with a metal ion. In such embodiments, the self-assembling molecule can be complexed with a suitable metal ion prior to administration. In other embodiments, the self-assembling molecule comprises a metal chelator complexed with a suitable metal ion (e.g., a paramagnetic metal ion or a radionuclide).
Suitable metal chelators include, for example, linear, macrocyclic, terpyridine, and N3S, N2S2, or N4 chelators (see also, U.S. Pat. No. 4,647,447, U.S. Pat. No. 4,957,939, U.S. Pat. No. 4,963,344, U.S. Pat. No. 5,367,080, U.S. Pat. No. 5,364,613, U.S. Pat. No. 5,021,556, U.S. Pat. No. 5,075,099, U.S. Pat. No. 5,886,142, the disclosures of which are incorporated by reference herein in their entirety), and other chelators known in the art including, but not limited to, HYNIC, DTPA, EDTA, DOTA, TETA, and bisamino bisthiol (BAT) chelators (see also U.S. Pat. No. 5,720,934). For example, macrocyclic chelators, and in particular N4 chelators are described in U.S. Pat. Nos. 4,885,363; 5,846,519; 5,474,756; 6,143,274; 6,093,382; 5,608,110; 5,665,329; 5,656,254; and 5,688,487, the disclosures of which are incorporated by reference herein in their entirety. Certain N3S chelators are described in PCT/CA94/00395, PCT/CA94/00479, PCT/CA95/00249 and in U.S. Pat. Nos. 5,662,885; 5,976,495; and 5,780,006, the disclosures of which are incorporated by reference herein in their entirety. The chelator may also include derivatives of the chelating ligand mercapto-acetyl-glycyl-glycyl-glycine (MAG3), which contains an N3S, and N2S2 systems such as MAMA (monoamidemonoaminedithiols), DADS (N2S diaminedithiols), CODADS and the like. These ligand systems and a variety of others are described in Liu and Edwards, Chem. Rev. 1999, 99, 2235-2268; Caravan et al., Chem. Rev. 1999, 99, 2293-2352; and references therein, the disclosures of which are incorporated by reference herein in their entirety.
The metal chelator may also include complexes known as boronic acid adducts of technetium and rhenium dioximes, such as those described in U.S. Pat. Nos. 5,183,653; 5,387,409; and 5,118,797, the disclosures of which are incorporated by reference herein, in their entirety.
Examples of suitable chelators include, but are not limited to, derivatives of diethylenetriamine pentaacetic acid (DTPA), 1,4,7,10-tetraazacyclotetradecane-1,4,7,10-tetraacetic acid (DOTA), 1-substituted 1,4,7-tricarboxymethyl 1,4,7,10 tetraazacyclododecane triacetic acid (DO3A), derivatives of the 1-1-(1-carboxy-3-(p-nitrophenyl)propyl-1,4,7,10 tetraazacyclododecane triacetate (PA-DOTA) and MeO-DOTA, ethylenediaminetetraacetic acid (EDTA), and 1,4,8,11-tetraazacyclotetradecane-1,4,8,11-tetraacetic acid (TETA), derivatives of 3,3,9,9-Tetramethyl-4,8-diazaundecane-2,10-dione dioxime (PnAO); and derivatives of 3,3,9,9-Tetramethyl-5-oxa-4,8-diazaundecane-2,10-dione dioxime (oxa PnAO). Additional chelating ligands are ethylenebis-(2-hydroxy-phenylglycine) (EHPG), and derivatives thereof, including 5-C1-EHPG, 5-Br-EHPG, 5-Me-EHPG, 5-t-Bu-EHPG, and 5-sec-Bu-EHPG; benzodiethylenetriamine pentaacetic acid (benzo-DTPA) and derivatives thereof, including dibenzo-DTPA, phenyl-DTPA, diphenyl-DTPA, benzyl-DTPA, and dibenzyl-DTPA; bis-2 (hydroxybenzyl)-ethylene-diaminediacetic acid (HBED) and derivatives thereof the class of macrocyclic compounds which contain at least 3 carbon atoms and at least two heteroatoms (O and/or N), which macrocyclic compounds can consist of one ring, or two or three rings joined together at the hetero ring elements, e.g., benzo-DOTA, dibenzo-DOTA, and benzo-NOTA, where NOTA is 1,4,7-triazacyclononane N,N′,N″-triacetic acid, benzo-TETA, benzo-DOTMA, where DOTMA is 1,4,7,10-tetraazacyclotetradecane-1,4,7,10-tetra(methyl tetraacetic acid), and benzo-TETMA, where TETMA is 1,4,8,11-tetraazacyclotetradecane-1,4,8,11-(methyl tetraacetic acid); derivatives of 1,3-propylenediaminetetraacetic acid (PDTA) and triethylenetetraaminehexaacetic acid (TTHA); derivatives of 1,5,10-N,N′,N″-tris(2,3-dihydroxybenzoyl)-tricatecholate (LICAM) and 1,3,5-N,N′,N″-tris(2,3-dihydroxybenzoyl)aminomethylbenzene (MECAM). Examples of representative chelators and chelating groups are described in WO 98/18496, WO 86/06605, WO 91/03200, WO 95/28179, WO 96/23526, WO 97/36619, PCT/US98/01473, PCT/US98/20182, and U.S. Pat. No. 4,899,755, U.S. Pat. No. 5,474,756, U.S. Pat. No. 5,846,519 and U.S. Pat. No. 6,143,274, each of which is hereby incorporated by reference in its entirety.
In some embodiments, the metal chelator comprises desferrioxamine (also referred to as deferoxamine, desferrioxamine B, desferoxamine B, DFO-B, DFOA, DFB or desferal) or a derivative thereof. See, for example U.S. Pat. No. 8,309,583, U.S. Pat. No. 4,684,482, and U.S. Pat. No. 5,268,165, each of which is hereby incorporated by reference in its entirety for its teaching of desferrioxamine and desferrioxamine derivatives.
As is well known in the art, metal chelators can be specific for particular metal ions. Suitable metal chelators can be selected for incorporation into the self-assembling molecule based on the desired metal ion and intended use of the self-assembling molecule.
Paramagnetic Ions
Paramagnetic ions form a magnetic moment upon the application of an external magnetic field thereto. Magnetization is not retained in the absence of an externally applied magnetic field because thermal motion causes the spin of unpaired electrons to become randomly oriented in the absence of an external magnetic field. By taking advantage of its property of shortening the magnetic relaxation time of water molecules, a paramagnetic substance is usable as an active component of MRI contrast agents. Suitable paramagnetic transition metal ions include Cr3+, Co2+, Mn2+, Ni2+, Fe2+, Fe3+, Zr4+, Cu2+, and Cu3+. In preferred embodiments, the paramagnetic ion is a lanthanide ion (e.g., La3+, Gd3+, Ce3+, Tb3+, Pr3+, Dy3+, Nd3+, Ho3+, Pm3+, Er3+, Sm3+, Tm3+, Eu3+, Yb3+, or Lu3+). In MRI, especially preferred metal ions are Gd3+, Mn2+,Fe3+, and Eu2+.
MRI contrast agents can also be made with paramagnetic nitroxides molecules in place of the chelating agent and paramagnetic metal ion.
Radionuclides
Suitable radionuclides include 99mTc, 67Ga, 68Ga, 66Ga, 47Sc, 51Cr, 167Tm, 141Ce, 111In, 123I, 125I, 131I, 124I, 18F, 11C, 15N, 17O, 168Yb, 175Yb, 140La, 90Y, 88Y, 86Y, 153Sm, 166Ho, 165Dy, 166Dy, 62Cu, 64Cu, 67Cu, 97Ru, 103Ru, 186Re, 188Re, 203Pb, 211Bi, 212Bi, 213Bi, 214Bi, 225Ac, 225At, 105Rh, 109Pd, 117mSn, 149Pm, 161Tb, 177Lu, 198Au, 199Au, 89Zr, and oxides or nitrides thereof. The choice of isotope will be determined based on the desired therapeutic or diagnostic application. For example, for diagnostic purposes (e.g., to diagnose and monitor therapeutic progress in primary tumors and metastases), suitable radionuclides include 64Cu, 67Ga, 68Ga, 66Ga, 99mTc, and 111In, 18F, 89Zr, 123I, 131I, 124I, 177Lu, 15N, 17O. For therapeutic purposes (e.g., to provide radiotherapy for primary tumors and metastasis related to cancers of the prostate, breast, lung, etc.), suitable radionuclides include 64Cu, 90Y, 105Rh, 111In, 131I, 117mSn, 149Pm, 153Sm, 161Tb, 166Dy, 166Ho, 175Yb, 177Lu, 186/188Re, 199Au, 131I, and 125I, 212Bi, 211At.
In the case of self-assembled molecules designed to be imaged using PET, radionuclides with short half-lives such as carbon-11 (˜20 min), nitrogen-13 (˜10 min), oxygen-15 (˜2 min), fluorine-18 (˜110 min), or rubidium-82 (˜1.27 min) are often used. In certain embodiments when a non-metal radionuclide is employed, the therapeutic or diagnostic agent comprises a radiotracer covalently attached to the self-assembling molecule. By way of exemplification, suitable 18F-based radiotracers include 18F-fluordesoxyglucose (FDG), 18F-dopamine, 18F-L-DOPA, 18F-fluorcholine, 18F-fluormethylethylcholin, and 18P-fluordihydrotestosteron.
In the case of self-assembled molecules designed to be imaged using PET, radionuclides with long half-lives such as 124I, or 89Zr are also often used.
Fluorophores
Fluorescent imaging has emerged with unique capabilities for molecular cancer imaging. Fluorophores emit energy throughout the visible spectrum; however, the best spectrum for in vivo imaging is in the near-infrared (NIR) region (650 nm-900 nm). Unlike the visible light spectrum (400-650 nm), in the NIR region, light scattering decreases and photo absorption by hemoglobin and water diminishes, leading to deeper tissue penetration of light. Furthermore, tissue auto-fluorescence is low in the NIR spectra, which allows for a high signal to noise ratio. There is a range of small molecule organic fluorophores with excitation and emission spectra in the NIR region. Some, such as indocyanine green (ICG) and cyanine derivatives Cy5.5 and Cy7, have been used in imaging for a relatively long time. Modern fluorophores are developed by various biotechnology companies and include: Alexa dyes; IRDye dyes; VivoTag dyes and HylitePlus dyes. In general, the molecular weights of these fluorophores are below 1 kDa.
Other Agents
In some embodiments, the therapeutic or diagnostic agent comprises a radiocontrast agent. In these embodiments the therapeutic agent can comprise an iodinated moiety covalently attached to the self-assembling molecule. Examples of suitable radiocontrast agents include iohexol, iodixanol and ioversol.
Disclosed are pharmaceutical compositions containing therapeutically effective amounts of one or more of the disclosed self-assembling molecules and a pharmaceutically acceptable carrier. The phrase “pharmaceutically acceptable” is employed herein to refer to those compounds, materials, compositions, and/or dosage forms which are, within the scope of sound medical judgment, suitable for use in contact with the tissues of human beings and animals without excessive toxicity, irritation, allergic response, or other problems or complications commensurate with a reasonable benefit/risk ratio. Pharmaceutical carriers suitable for administration of the molecules provided herein include any such carriers known to those skilled in the art to be suitable for the particular mode of administration.
In some cases, formulations contain exclusively one type of self-assembling molecule. In other cases, the formulations include a mixture of two or more self-assembling molecules. For example, in some embodiments, the formulation contains a portion of self-assembling molecules bound to diagnostic agents and a portion that is free of diagnostic agents. The optimal ratio of bound and unbound molecules can be determined empirically by ordinary skill.
The self-assembling molecules can be formulated for a variety of routes of administration and/or applications. For use in conjunction with the treatment and/or diagnosis of tumors, the self-assembling molecules are preferably administered by injection intravenously or intraparentoneally for tumor imaging. The self-assembling molecules can also be administered by alternative parenteral routes which are suitable to achieve tumor localization and self-assembly. For example, the self-assembling molecules can be administered into and/or around a tumor in, for example, sentinel lymph node identification. A non tumor example would be intrasynovial administration to evaluate inflammation in inflamed acidic joint spaces Subcutaneous administration could be used to evaluate the tumorogenic status of lymph nodes.
Suitable dosage forms for parenteral administration include solutions, suspensions, and emulsions. Typically, the self-assembling molecules are dissolved or suspended in a suitable solvent such as, for example, water, Ringer's solution, phosphate buffered saline (PBS), or isotonic sodium chloride. The formulation may also be a sterile solution, suspension, or emulsion in a nontoxic, parenterally acceptable diluent or solvent such as 1,3-butanediol.
Formulations may further include one or more additional excipients. Representative excipients include solvents, diluents, pH modifying agents, preservatives, antioxidants, antinfective agents, suspending agents, wetting agents, viscosity modifiers, tonicity agents, stabilizing agents, and combinations thereof. Suitable pharmaceutically acceptable excipients are preferably selected from materials which are generally recognized as safe (GRAS), and may be administered to an individual without causing undesirable biological side effects or unwanted interactions.
In some cases, formulations can include one or more tonicity agents to adjust the isotonic range of the formulation. Suitable tonicity agents are well known in the art and include glycerin, mannitol, sorbitol, sodium chloride, and other electrolytes.
In some cases, the formulations can be buffered with an effective amount of buffer necessary to maintain a pH suitable for parenteral administration. Suitable buffers are well known by those skilled in the art and some examples of useful buffers are acetate, borate, carbonate, citrate, and phosphate buffers.
In some instances, the formulation is distributed or packaged in a liquid form. Alternatively, formulations for ocular administration can be packed as a solid, obtained, for example by lyophilization of a suitable liquid formulation. The solid can be reconstituted with an appropriate carrier or diluent prior to administration.
If desired, formulations can contain one or more radiostabilizers to slow or prevent radiolytic damage to components of the composition. Formulations may be liquid or in lyophilized form using lyophilation agents such as sorbitol or mannitol, and such agents would be redissolved in water for injection, dextrose, saline or phosphate buffered saline or other suitable injectable, sterile liquid. Injectable formulation of these self assembling diagnostic or therapeutic self assembling molecules can be made sterile and pyrogen free by methods known in the pharmaceutical art.
The disclosed self-assembling molecules that accumulate within acid tissue, such as tumors or inflamed joints, may be used to diagnose or treat a condition characterized by the acid tissue (e.g., tumors or inflammation) in subjects. Therefore, disclosed is a method for diagnosing cancer in a subject that involves first administering to the subject an effective amount of a composition containing a plurality of the disclosed biocompatible self-assembling molecules conjugated to a diagnostic agent, and then imaging the subject for the presence of the diagnostic agent, wherein detection of an accumulated amount of the diagnostic agent in the subject is an indication of the presence of a tumor.
The term “accumulated amount” generally refers to an amount sufficient detect the diagnostic agent against background levels. For example, a concentration of diagnostic agent at least 20%, 30%, 40%, 50%, 60%, 70%, 80%, 90%, or 100% higher than background levels can be sufficient for detection.
Imaging technologies are known in the art and include without limitation X-ray radiography, ultrasound, computed tomography (CT), single-photon emission computed tomography (SPECT), magnetic resonance imaging (MRI), positron emission tomography (PET), Optical imaging and nuclear medicine. When the appropriate diagnostic agent is present in the disclosed self-assembling molecules, these technologies may be used to detect accumulated self-assembling molecules within tumors.
Also disclosed is a method for treating cancer in a subject that involves administering to the subject a composition containing a plurality of the disclosed biocompatible self-assembling molecules conjugated to a therapeutic agent, wherein therapeutic agent accumulates in the cancer of the subject in a therapeutically effective amount and treats the cancer.
For example, the therapeutic agent can comprises a radionuclide suitable for targeted radionuclide tumor therapy. In targeted radionuclide therapy, the biological effect is obtained by energy absorbed from the radiation emitted by the radionuclide. Whereas the radionuclides used for nuclear medicine imaging emit gamma rays, which can penetrate deeply into the body, the radionuclides used for targeted radionuclide therapy must emit radiation with a relatively short path length. There are three types of particulate radiation of consequence for targeted radionuclide therapy—beta particles, alpha particles, and Auger electrons, which can irradiate tissue volumes with multicellular, cellular and subcellular dimensions, respectively. In some cases, mixed emitters are used to allow both imaging and therapy with the same radionuclide (e.g., the mixed beta/gamma emitter, iodine-131 and 177Lu). Moreover, within each of these categories, there are multiple radionuclides with a variety of tissue ranges, half-lives, and chemistries, offering the attractive possibility of tailor-making the properties of a targeted radionuclide therapeutic to the needs of an individual patient.
The range of alpha particles in tissue is only a few cell diameters, offering the prospect of matching the cell-specific nature of molecular targeting with radiation of a similar range of action. Another attractive feature of alpha particles for targeted radionuclide therapy is that, as a consequence of their high linear energy transfer, they may have greater biological effectiveness per nuclide than either conventional external beam x-ray radiation or beta emitters. Studies performed in cell culture have demonstrated that human cancer cells can be killed even after being hit by only a few alpha particles and that unlike other types of radiation, where oxygen is necessary for free radicals to be generated, efficient cancer cell elimination can be achieved even in an hypoxic environment. Phase I clinical trials have been performed with bismuth-213- and astatine-211-labeled monoclonal antibodies in patients with leukemia and brain tumors, respectively, and radium-223 is being evaluated in breast and prostate cancer patients with bone metastases.
Currently, the targeted radiotherapeutics approved by the FDA for human use are limited to four beta emitters: yttrium-90 and iodine-131, which are used in tandem with monoclonal antibodies to treat non-Hodgkin's lymphoma, and samarium-153-EDTMP (Quadramet®) and strontium-89-chloride for palliation of bone metastases. However, the scope of preclinical and clinical research in the therapy field is much broader, involving at least eight additional beta-emitting radionuclides: lutetium-177, holmium-166, rhenium-186, rhenium-188, copper-67, promethium-149, gold-199, and rhodium-105.
Auger electron emitters, such as bromine-77, indium-111, iodine-123, and iodine-125, may also be used for radiotherapy. When used in concert with targeting vehicles that can localize these subcellular-range radiations in close proximity to cellular DNA, studies in cell culture have shown highly effective and specific tumor cell killing.
In some embodiments, the method further comprises administering to the subject a composition containing a radiosensitizer. Examples of known radiosensitizers include gemcitabine, 5-fluorouracil, pentoxifylline, and vinorelbine.
In some embodiments, the self-assembling molecule comprises a metal chelator uncomplexed with a metal ion. In such embodiments, methods may further involve complexing the metal chelator with a suitable metal ion prior to administration.
Tumors
The tumor of the disclosed methods can be any tissue in a subject undergoing unregulated growth, invasion, or metastasis, and having a relatively acidic extracellular microenvironment. Most cancers heavily use glycolytic metabolism to a greater extent than do normal tissues. Glycolytic metabolism produces excess protons and lactic acid in the extracellular spaces of the tumor and its immediate surroundings, which lowers the pH from physiologic 7.4. Generally, the more aggressive cancers produce greater quantities of acid and lower extracellular pH environments. Therefore, in some embodiments, the tumor is any tissue that preferentially uptakes fluorodeoxyglucose (18F-FDG). For example, the tumor can be Hodgkin's disease, non-Hodgkin's lymphoma, colorectal cancer, breast cancer, renal cancer, melanoma, or lung cancer. In some embodiments, the cancer is prostate cancer, which does not have preferential uptake of 18F-FDG.
In some aspects, the tumor of the disclosed methods is a neoplasm for which radiotherapy is currently used. The tumor can also be a neoplasm that is not sufficiently sensitive to radiotherapy using standard methods. The tumor can be a sarcoma, lymphoma, carcinoma, blastoma, or germ cell tumor. A representative but non-limiting list of cancers that the disclosed compositions can be used to treat include B cell lymphoma, T cell lymphoma, mycosis fungoides, Hodgkin's Disease, bladder cancer, brain cancer, nervous system cancer, head and neck cancer, squamous cell carcinoma of head and neck, kidney cancer, lung cancers such as small cell lung cancer and non-small cell lung cancer, adenocarcinoma, liposarcoma, neuroblastoma/glioblastoma, ovarian cancer, pancreatic cancer, prostate cancer, skin cancer, liver cancer, melanoma, squamous cell carcinomas of the mouth, throat, larynx, and lung, colon cancer, cervical cancer, cervical carcinoma, breast cancer, epithelial cancer, renal cancer, genitourinary cancer, pulmonary cancer, esophageal carcinoma, head and neck carcinoma, large bowel cancer, hematopoietic cancers; testicular cancer; colon and rectal cancers, prostatic cancer, and pancreatic cancer.
Administration
The exact amount of the compositions administered to a patient will vary from subject to subject, depending on the nature of the diagnostic or therapeutic agent (e.g., type of imaging employed, nature of the agent, etc.), the species, age, weight and general condition of the subject, the mode of administration and the like. It will also depend on the imaging modality for which the invention has been constructed. Doses for diagnostic imaging are generally in decreasing order: X ray>MRI>Optical>nuclear. For example, X-ray imaging can involve accumulating about 1-2 mM iodine at the tumor site. MRI can be approximately 10 times lower. Optical Fluorescence imaging can be about 5-10 times lower than MRI, and nuclear mass doses can be lower than nuclear, and dependent mostly on the nuclear radioactive dose rather than the mass dose.
For example, a self assembling diagnostic agent for MRI can contain a chelating agent which is bound tightly to a paramagnetic metal such as Gd3+. In this mode the dose of the agent can be about 0.025-0.3 mmol/kg. When imaging will be via PET using 68Ga as the positron emitting nuclide, the chelating agent could again be used, optionally adjusted for the size difference between Ga3+ and Gd3+, and the radioactive dose could be about 2-5 mCi for a human 70 kg patient. Veterinary dosing would depend primarily on the weight of the veterinary patient, with, for example, a 70 kg porcine patient receiving about the same dose as a 70 kg human.
In another embodiment, nuclear medicine diagnostics are performed using 18F or 124I nuclides. In these cases, the chelating agent can be replaced with an aliphatic, or aromatic group, respectively, for standard radiolabeling with these halogens, respectively. The dosage for imaging with PET can be approximately similar to dosage used for 68Ga. For radiotherapy, a self-assembling molecule using a metal chelator, for example to chelate 177Lu, can be delivered in monthly doses of an empirically determined amount which spares (or minimizes the damage to) normal tissues but otherwise was maximized for tumor killing. The target organ for these self assembling molecules can include bone marrow, liver and GI systems. Maximal human single doses can be as high as possible, but at least 50 mCi/month, and preferably up to 300 mCi/month. Generally in nuclear medicine diagnostics and therapeutics, the mass dose (mass/kg) is lower than in non-nuclear imaging such as X ray, MRI and Optical imaging. See, for example, Sovak M. ed. Radiocontrast Agents. New York: Springer-Verlag, 1984: Handbook of Experimental Pharmacology Volume 73. 1984; Tweedle M F. Relaxation Agents in NMR Imaging. In J.-C. G. Bunzli, G. R., ed. Lanthanide Probes in Life, Chemical and Earth Sciences, Theory and Practice. Amsterdam: Elsevier, 1989: 127-179; Merbach A E; Toth E; eds. The Chemistry of Contrast Agents in Medical Magnetic Resonance Imaging. Wiley, 2001. Nuclear: Sandler M P, Coleman R E, Patton J A, Wackers F J th, Gottschalk A, eds. Diagnostic Nuclear Medicin, 4th Edition, Lippincott Williams Wilkins. 2003. And in Radiotherapy, Speer T W; Targeted Radionuclide therapy, Wolters Kluwer, 2011.
Effective dosages and schedules for administering the compositions may be determined empirically, and making such determinations is within the skill in the art. The dosage ranges for the administration of the compositions are those large enough to produce the desired effect (e.g., a therapeutic result or a suitable diagnostic result). The dosage should not be so large as to cause adverse side effects, such as unwanted cross-reactions, anaphylactic reactions, and the like. Generally, the dosage will vary with the age, condition, sex and extent of the disease in the patient, route of administration, or whether other drugs are included in the regimen, and can be determined by one of skill in the art. The dosage can be adjusted by the individual physician in the event of any counterindications.
There has been much interest in understanding the influence of size, shape, and mechanical properties of nanomaterials on their biodistribution, to design more effective drug delivery and imaging agents. For example, the enhanced permeation and retention of spherical materials with 20-200 nm diameters in the leaky, non-lymphatic vasculature of tumor tissue has ultimately led to the development of FDA-approved liposomal therapies (Torchilin, V. P. Nat. Rev. Drug Discov. 2005 4:145-60; Matsumura, Y. et al. Cancer Res. 1986 46:6387-92). More recently, the size and shape of nanomaterials has been found to play a significant role in the distribution and circulation lifetimes of these objects when delivered intraveneously (Geng, Y., et al. Nat. Nanotech. 2007 2:249-55; Petros, R. A., et al. Nat. Rev. Drug Discov. 2010 9:615-27; Yoo, J.-W., et al. Nat. Rev. Drug Discov. 2011 10:521-35; Popovic, Z., et al. Angew. Chem. Int. Ed. 2010, 49, 8649-52). For example, cylindrical polymeric micelles have been shown to have a ten times longer circulation time in the bloodstream compared to their spherical counterparts (Geng, Y., et al. Nat. Nanotech. 2007 2:249-55). Still, most of these materials tend to be either static objects that do not transform in the cancer environment or carriers that fragment into smaller objects to release cargo when they get to the target (Sawant, R. M., et al. Bioconjugate Chem. 2006 17:943-49; Torchilin, V. P. Pharm. Res. 2007 24: 1-16).
Designing nanomaterials that can spontaneously change shape and size in response to specific physiological stimuli has the potential to exploit the differential diffusion kinetics to amplify the accumulation of these agents. For cancer, one particularly attractive stimulus is the slightly acidic extracellular microenvironment of tumor tissue (pH 6.6-7.4) (Gatenby, R. A., et al. Nat Rev Cancer 2004 4:891-99) that arises due to the enhanced rate of glycolysis (Hanahan, D., et al. Cell 2011 144:646-74). There are numerous examples of materials that incorporate acid-cleavable linkages that degrade under the lysosomal (pH 5.0-5.5) or the slightly acidic tumor environment to release cargo (Sawant, R. M., et al. Bioconjugate Chem. 2006 17:943-49; Torchilin, V. P. Pharm. Res. 2007 24: 1-16), however, there are far fewer examples of materials that reversibly transform to larger, more slowly diffusing morphologies in response to the extracellular cancer pH. The notion of creating a material that, upon reaching the acidic extracellular tumor environment, transforms into a bulky, more slowly diffusing object could serve as a mechanism for achieving a higher relative concentration of imaging, drug delivery, or radiotherapeutic agent at the tumor site compared to the bloodstream. Although a multitude of self-assembling materials have pH-dependent assembly behavior, there are very few biologically compatible systems designed for in vivo use, with assembly behavior that can be reversibly triggered at neutral pH values (6.6-7.4) in an ionic environment that resembles serum. Both the concentration and the valency of the ionic environment plays a key role in mediating the self-assembly of charged systems (Hiemenz, P. C., et al. Rajagopalan, R. Principles of Colloid and Surface Chemistry; 3rd ed., 1997). Thus, developing systems that function under the stringent set of conditions for in vivo use requires a considerable amount of insight and optimization.
Results
To develop materials capable of reversible pH-triggered morphological changes, amphiphilic molecules that exist as either single molecules or spherical micelles under normal physiological conditions (pH=7.4) but self-assemble into nanofibers upon encountering the acidic environment (pH=6.6) of the tumor vasculature were designed (
PA 5 had the following structure:
A PA design strategy was developed for tuning the pH at which the self-assembly transition into nanofibers occurs by tenths of pH units, in simulated serum salt solutions (150 mM NaCl, 2.2 mM CaCl2) (In The Merck Manual of Diagnosis and Therapy; 19th edition ed.; Porter, R. S., Kaplan, J. L., Eds.; Merck Publishing Group: 2011). It was a goal to develop Gd3+-based magnetic resonance imaging agents, and 10 μM is the minimum diagnostic concentration of these agents in blood (Nunn, A. D., et al. J. Nucl. Med. 1997 41:155-62; Wedeking, P., et al. Magn. Reson. Imag. 1999 17:569-75). The PAs in this study contain a palmitic acid tail; an XAAA (SEQ ID NO:38) β-sheet-forming region, where X is an amino acid with a nonpolar side chain; and four glutamic acid residues (Table 1). A ratio of one strongly hydrophobic amino acid (e.g., Tyrosine (Y), Valine (V), Phenylalanine (F), or Isoleucine (I)) to four glutamic acids enabled transition in the desired pH range of 6.0-6.6. PAs were synthesized by solid-phase Fmoc synthesis, and purified by reverse-phase high-performance liquid chromatography (HPLC). Their purity was assessed using analytical HPLC, electrospray ionization mass spectrometry (ESI-MS), and peptide content analysis.
The target PA concentration (10 μM) was below the detectable limit of conventional techniques to determine the morphology such as cryoTEM and small-angle X-ray scattering. Consequently, circular dichroism (CD) spectroscopy was initially used to characterize the morphology of these PAs at various pH values. PA 1 was the first molecule synthesized that underwent a self-assembly transition in the desired pH range of 6.6-7.4 at 10 μM PA concentration, in 150 mM NaCl and 2.2 mM CaCl2 (
The transition between random coil and β-sheet structure was rapid and reversible. At a pH of 7.75, HCl was added until the pH was 6.1, and the resulting β-sheet CD spectrum was collected within three minutes. An appropriate amount of NaOH was then added to reverse the pH back to 7.70, and random coil behavior was observed again. This process was repeated three times and the CD spectra were found to be superimposable with respect to pH (
When the CD spectra show a random coil morphology, the PA molecules could either be self-assembled into spherical micelles or exist as isolated molecules in solution (Goldberger, J. E., et al. Angew. Chem. Int. Ed. 2011 50:6292-95). Because it is difficult to distinguish between staining artifacts and sample with TEM imaging at such a low concentration of sample, to determine the morphology under basic pH values, the critical aggregation concentration (CAC) was measured for PA 1 at pH=6.6 using the pyrene 1:3 method (
To determine the overall influence of concentration and pH on the nature of this self-assembly transition, CAC measurements were performed at pH values between 4.0 and 10.0 (
By varying the β-sheet propensity of the amino acids in the β-sheet forming region, the transition pH can be systematically tuned. In PAs 2-4, the isoleucine of PA 1 was substituted with the hydrophobic amino acids phenylalanine, valine, and tyrosine. pH dependent CD spectra of PAs 2-4 at 10 μM, also showed a β-sheet to random coil transition at pH's between 6.0-6.6 (
An MRI imaging moiety was then incorporated on the C-terminus of the PA. An additional lysine, conjugated to a 1,4,7-tris(carboxymethylaza)cyclododecane-10-azaacetylamide (DO3A) tag was linked to the C-terminus of PA 1 and PA 3 to produce PA 5 and PA 6. The molecule-to-nanofiber transition was still observed at 10 μM PA concentration, however the transition pH of PA 5 was shifted to 5.7 (
The concentration-pH self-assembly phase diagram was mapped out for PA 5 (
The shift in transition pH due to the change in β-sheet propensity still occurred when the Gd(DO3A) moiety was present. For each concentration, PA 6 had a nanofiber to micelle transition that occurred at 0.4 units lower than PA 5 (
Relaxivity values of water protons in the presence of PA 5 at 500 μM, at pH 4 and pH 10 were found to be 8.3 and 6.6 mM−1 s−1, using a 1.5 T magnet. These values were higher than that which we measured for a Magnevist control standard (4.5 mM−1 s−1) (Stanisz, G. J., et al. Magn. Reson. Med. 2000 44:665-67; Sasaki, M., et al. Magn. Res. Med. Sci. 2005 4:145-9). This relaxivity increase from spherical micelles to nanofibers likely originates from the longer rotational correlation time when imaging agents are coupled to large molecular weight objects, which has been well-established for magnetic resonance agents coupled to polymers and peptide amphiphiles (Bull, S. R., et al. Nano Letters 2005 5:1-4; Bull, S. R., et al. Bioconjugate Chem. 2005 16:1343-48; Nicolle, G. M., et al. J. Biol. Inorg. Chem. 2002 7:757-69). The relaxivity of these systems was about 25-50% lower than other supramolecular assemblies with similar K(DO3A:Gd) linkages (Bull, S. R., et al. Nano Letters 2005 5:1-4; Accardo, A., et al. Coord. Chem. Rev. 2009, 253, 2193-213). This suggests that the Gd(DO3A) motion is independently faster than that of the nanofiber due to the conformationally flexible E4K tether, which can be further optimized. Regardless, the primary mechanism for tumor imaging relies on the increased local concentration of the more slowly diffusing nanofibers in the tumor environment compared to the blood stream, but the improved relaxivity of fibers compared to spheres could serve as a secondary mechanism for enhanced tumor detection.
In summary, through judicious design it is possible to use the power of self-assembly to develop dynamic materials that change shape and size in response to slight changes in pH, in solutions that have monovalent and divalent ion concentrations similar to those of serum. This morphological change is rapid, reversible, and occurs under thermodynamic equilibrium, which is ideal for in vivo imaging and drug delivery applications. The molecules presented here outline a design strategy for precisely tuning self-assembly behavior.
Materials and Methods
Synthesis of Exemplary Peptide Amphiphiles (PAs):
All amino acids were purchased from AnaSpec Inc. unless otherwise specified. The peptides were synthesized by the solid-phase technique using standard Fmoc chemistry. For PAs containing lysine, Sieber resin (AAPPTEC) was used; all other peptides were synthesized using Rink Amide resin (AAPPTEC). Peptides that were made on a 0.25 mmol-scale, were synthesized on an automated peptide synthesizer (Applied Biosystems Model No. 433A) with Applied Biosystem cartridges for all but palmitic acid (Sigma Aldrich). Peptides above 0.25 mmol were synthesized manually as described in the following paragraph.
The resin was swollen in a shaker vessel with dichloromethane (DCM) for 30 minutes, the DCM was removed and dimethyl formamide (DMF) was added, followed by mechanically shaking the mixture for 30 minutes. For deprotection, 20% piperidine in DMF was used to remove the Fmoc protecting group on the resin. A Kaiser test protocol confirmed removal of the Fmoc protecting group. Coupling of the amino acid to the amine end of the resin was done through activation using either O-Benzotriazole N,N,N′,N′-tetramethyluronium hexafluorophosphate (HBTU) or 2-(7-Aza-1H -benzotriazole-1-yl)-1,1,3,3-tetramethyluronium hexafluorophosphate (HATU). The coupling solution contained 3.96 Eqv. of amino acid, 4 Eqv. of HBTU/HATU, 4 Eqv. of N-Hydroxybenzotriazole (HOBt) or 1-Hydroxy-7-azabenzotriazole (HOAt), and 8 Eqv. of Diisopropyl ethylamine (DIPEA) with respect to peptide allowing at least 3 hours of coupling per amino acid. The surfactant Triton X-100 was added to the coupling solution and to the latter amino acids to aid in coupling efficiency. Resin cleavage of the peptide was done by addition of the following solutions: For the Rink Amide resin, a solution of 95% Trifluoroacetic acid (TFA), 2% Anisole, 2% water was used and for Sieber Resin cleavage, a solution of 1% TFA, 2% Anisole, 1% Triisopropyl silane (TIS) and 96% DCM was used; shaken for at least 2 hours. The TFA was removed under vacuo and the PA was precipitated using two 20 mL portions of cold diethyl ether. The crude peptide was filtered and washed with cold diethyl ether.
Purification of Peptide Amphiphiles:
The crude peptide amphiphile was dissolved in 0.1% NH4OH solution at approximately 10 mg/mL concentration by vigorously shaking and sonicating until the solution turned clear. To aid in dissolution, an additional drop of concentrated NH4OH was added to the solution. The PA solution was filtered first using a 0.45 μm syringe filter (Whatman), followed by filtration through a 0.2 μm syringe filter. The sample was then purified on a Shimadzu preparative HPLC system (dual pump system controlled by LC-MS solution software) with an Agilent PLRP-S polymer column (Model No. PL1212-3100 150 mm×25 mm) under basic conditions. The product was eluted with a linear gradient of 10% Acetonitrile to 100% Acetonitrile over 30 minutes containing 0.1% NH4OH (v/v). The purity of the collected fractions was verified using an electrospray ionization time-of-flight mass spectrometer (Bruker) and a Shimadzu analytical HPLC system. Fractions greater than 90% purity were combined; the Acetonitrile (MeCN) was removed by vacuum before freeze-drying.
Synthesis and Purification of Protected Tri-Tert-Butyl Ester DO3A Derivative:
The synthesis scheme for a protected tri-tert-butyl ester DO3A derivative is shown in
Attachment of DO3A to Peptide Amphiphiles:
To attach the DO3A derivative, an additional Lysine (K) with its side chain amine protected by a methyl trityl group, was coupled to the PA sequence after the last glutamic acid (E). The cleavage cocktail used to cleave the PA from the Sieber resin also removed the methyl trityl group from the lysine. The DO3A was then coupled to the side chain amine group of the lysine in solution phase using the coupling solution mentioned earlier (synthesis of peptide amphiphiles) with the exception of 1 eqv. of the tri-tert-butyl ester DO3A derivative.
Incorporation of Gd3+ in the PA-DO3A Conjugates:
2.27 mg of the previously prepared PA-DO3A conjugate was dissolved in 1.0 mL of water and combined with 2 eq. of GdCl3 in 0.01 M HCl. The reaction was set to stir in an oil bath at 60° C. for 30 min. The pH of the solution was gradually adjusted from approximately pH 2 to pH 4-5 using small amounts of 0.050 M NaOH. The resultant solution was stirred for 24 hours at 60° C. A small sample was removed and analyzed by MALDI-MS to determine the extent of reaction completion. The pH was then raised to 8-9 over a period of an hour using ammonium hydroxide (to precipitate excess Gd3+ as Gd(OH)3) followed by the addition of EDTA (to chelate excess free Gd3+) and filtered using a 0.2 μm syringe filter. The solution was dialyzed against Millipore water to remove NaCl, free Gd3+, and EDTA-Gd3+. The buffer water for dialysis was changed 4 times over a period of 24 hours. The PA-DOTA-Gd3+ solution was finally freeze-dried to recover a white fluffy powder.
Peptide Content Analysis:
Peptide content analysis was performed on lyophilized samples to verify the amino acid stoichiometry and determine the residual salt concentration for PA 1-5. The relative residue stoichiometry was within ±5% of the expected values for all amino acids in PA 1-5. The mg of total peptide amphiphile/mg of solid is listed in Table 3 below. All further CAC and CD measurements were scaled by these factors to determine the true concentration.
Circular Dichroism (CD) Spectroscopy:
Measurements were done on a Jasco-815 Circular Dichroism spectrometer using 1 cm path length quartz cuvettes. 10 μM solutions of peptide amphiphiles were prepared in 150 mM NaCl and 2.2 mM CaCl2 by dilution from a concentrated PA stock (0.5-1 mM, pH 9). Double deionized Milli-Q water was used for preparing all solutions. The solutions were then heated at 80° C. for 30 minutes in a water bath and gradually cooled to room temperature. An Accumet XL15 pH meter (Fisher Scientific) coupled with an Orion Ross Ultra semi-micro electrode (8103BNUWP, Thermo Scientific) was used to adjust the pH of the solution to the desired value followed by collection of the CD spectra Each trace shown was averaged over 3 accumulations and was baseline subtracted using aqueous solutions containing salts only. All spectra are cut-off below 205 nm due to absorption by NaCl and CaCl2.
Transmission Electron Microscopy (TEM):
TEM images were obtained using solutions of either 10 μM or 0.5 mM peptide amphiphile concentration, as well as 150 mM NaCl and 2.2 mM CaCl2 in Milli-Q water. The solutions were first heated at 80° C. for 30 minutes in a water bath and then gradually cooled to room temperature. This was followed by pH adjustment using either HCl or NaOH. 5 μL of this solution was pipetted onto a Carbon Formvar grid (Electron Microscopy Sciences) and allowed to sit for 2 minutes before being wicked dry using filter paper. For the 10 μM experiments that were performed to determine the time dependence of nanofiber formation, solutions were dropcast onto the grid within three minutes of pH adjustment. The samples were then negatively stained using 1 wt % uranyl acetate and imaged under a FEI Tecnai G2 Bio TWIN TEM system, operating at 100 kV. All TEM experiments were performed in triplicate, using at least three different freshly prepared solutions and grids.
pH Titration of Peptide Amphiphiles:
The titration measurements were conducted on 10 μM peptide amphiphile solutions prepared in 150 mM NaCl and 2.2 mM CaCl2 using milli-Q water. The solution was heated at 80° C. for 30 minutes followed by slow cooling at room temperature. The pH of the solution was then adjusted to 4 using HCl. Finally, an Accumet XL15 pH meter (Fisher Scientific) coupled with an Orion Ross Ultra semi-micro electrode (8103BNUWP, Thermo Scientific) was used to track changes in pH of the solution as NaOH solution was added in small increments. pKa values were obtained from the second inflection points of the first derivative plots of the titration data. The first transition corresponds to neutralization of excess HCl. The calculated pKas reflect the average pKa for all four glutamic acids.
Critical Aggregation Concentration (CAC) Determination Using the Pyrene 1:3 Method:
For the CAC measurements, a series of solutions of the PA with concentrations ranging from 10 nM to 300 μM were prepared using serial dilutions in 150 mM NaCl and 2.2 mM CaCl2. The final concentration of pyrene in each solution was fixed to be 1.23 μM. This was followed by pH adjustment of the solutions using careful additions of HCl or NaOH. 70 μL of each solution was transferred to a 96-well plate and the fluorescence emission of pyrene was monitored using a hybrid reader fluorimeter (BioTek Synergy H4) at room temperature. The excitation wavelength was set at 335 nm. The ratio of the intensities of emissions at 376 nm and 392 nm were then plotted as a function of the PA concentration (log scale). The CAC was determined from an abrupt change in the slope of the plot using the least-squares fitting technique.
Molecular Simulations:
The molecular length was estimated through models derived from the MM+ geometry optimization as implemented using the Hyperchem Software Suite. The molecule length was derived from the energy-minimized geometry of the fully extended molecule. The value for molecular length was assumed to be the distance between the final C atom on the alkyl chain and the end amide C atom on the terminal glutamic acid (for PAs 1-4).
Magnetic Resonance Imaging (MRI) Measurements:
An MR relaxometry phantom was built by fixing 5 mm NMR sample tubes containing PA samples at a concentration of 500 μM and pH values 4 and 10 in a 600 ml beaker filled with deionized water. The samples also contained 150 mM NaCl and 2.2 mM CaCl2. The phantom was scanned on a 1.5 Tesla Signa Excite MRI scanner using an 8-channel phased-array head coil (GE Healthcare, Milwaukee, Wis., USA). R1 relaxometry data were acquired using an Inversion Recovery Fast Spin-Echo (IR-FSE) sequence with the following parameters: inversion time TI=50/100/200/400/600/800/1200/1600/3200 ms; repetition time TR=8000 ms; echo time TE=11 ms; echo train length=10; 90° flip angle; 100×100 mm2 field-of-view (FOV); 0.5 mm in-plane resolution; 2 mm slice thickness; single coronal slice placed at the center of the phantom. Sample longitudinal relaxation rates (R1) were calculated by fitting the MR signal intensities observed at different TIs (S(TI)) to a three parameter model [Lu et al., MRM 2004]:
S(TI)=|S0×(1−C×exp(−TI×R1))|
Where S0 is the equilibrium signal, C is a constant accounting for imperfect inversion of magnetization. The r1 relaxivity was calculated as the slope in the linear relationship between sample concentrations and their R1 relaxation rates.
Pan-cancer biocompatible diagnostic (or theranostic) imaging agents or therapeutic agents that circulate through the bloodstream as isolated molecules or self assembled micelles of hydrodynamic diameter >10 nm that spontaneously and reversibly transform into long cylindrical nanofibers >100 nm only when encountering the extracellular acidic (pH 6.4-7.3) tumor microvasculature were designed. Because of the significantly slower diffusion constant of cylindrical nanofibers >1000 nm in length, the imaging agent is expected to significantly accumulate in the acidic tumor, which continuously resupplies its microenvironment with protons.
Peptide amphiphiles (PAs) were designed to contain a particular sequence of amino acids, lipids, a DO3A agent designed to bind to trivalent metal ions such as Gd3+ (for MRI), Lu3+ (for 177Lu radiotherapy), Tb3+ (for fluorescent analysis), and Ga3+ or In3+ (for 68Ga PET/CT or PET/MRI or 111In SPECT/CT), and with or without an ethylene glycol shell, that can undergo this transformation in a simulated blood environment (150 mM NaCl, 2.2 mM CaCl2). The pH of this transition at any particular concentration can occur between 5.1 and 7.3.
Numerous peptide amphiphiles have been synthesized and studied in the past; however these systems completely and irreversibly assemble into nanofibers that have with lengths that are >100 nm. Here, PAs were designed in such a way that the attractive supramolecular forces (hydrophobic-hydrophobic interactions, β-sheet formation) and the repulsive supramolecular forces (electrostatic repulsion, sterics) of the molecule are precisely balanced. The repulsive forces can be increased by increasing the number of charged amino acid residues, or adding a unit with larger hydrophilicity or greater steric hindrance such as a K(DO3A)2−. Increasing the attractive forces can be done by using longer alkyl chains, as well as increasing the number of β-sheet forming residues
Indeed, the pH at which a molecule undergoes this transition depends on the relative ratio of the standard peptide amphiphile molecule, which can contain the following components;
(Cn)—(BoUp)—(NqK(DO3A:M3+))-(PEG)r-propionic amide;
(Cn)—(BoUp)—(Nq-1K(DO3A:M3+))-(PEG)r-propionic acid;
(Cn)—(BoUp)—(NqK(DO3A:M3+))-NH2; or
(Cn)—(BoUp)—(Nq-1K(DO3A:M3+))-COOH;
where Cn=lipid tail with n carbons such as C16=palmitoyl, C14=myristoyl (n=12-18).
In the β-Sheet Forming Region
B=an amino acid with high β-sheet propensity (o=1 or 2)
U=an uncharged amino acid that with poor β-sheet propensity
Note that the order of B to U does not strongly affect the transition.
In the Charged Region
N=an anionic amino acid (q=3-7)
K(DO3A:M3+)=a lysine with a conjugated to a 1,4,7-tris(carboxymethylaza)cyclododecane-10-azaacetylamide tag M3+=Gd3+ for MRI
The order of N to K(DO3A:M3+) does not strongly affect the transition.
Also, the order of B:U:N:K(DO3A:M3+) does not strongly affect the transition
To Minimize Immune Response
PEG=ethylene glycol (r=0-8); (also branched PEG)
The amino acids are classified into the table below. The chirality of the amino acids can be either d-, or l- with minimal change of properties
For example, the peptide amphiphile molecule can be C16VAAAEEEEK(DO3A:Gd)-PEG-propionic amide (SEQ ID NO:6 for underlined portion), which has the following structure:
The most important factor for enabling this transition in a simulated serum environment lies with optimizing the n:o:q ratio.
n:o:q=16-17:1:3-4 with Amide Termination
In some cases, PAs having a C16 (palmitoyl) or a C17 (heptadecanoyl) chain (n=16-17) and one B amino acid (o=1), need 3-4 N amino acids (q=3-4). Also this transition can occur in the presence or absence of an ethyleneglycol-propionic amide tail with r=0-6.
The following PAs were synthesized and characterized for phase transition in simulated serum environment (150 mM NaCl, 2.2 μM CaCl2);
The Phase diagrams were determined using a combination of circular dichroism measurements and critical micelle measurements as shown below.
In these above PA sequences the most critical factor for fine-tuning the transition lies with the relative β-sheet propensity. By varying B with β-sheet propensity the transition pH can be fine-tuned.
The order of B to U and number of U amino acids is not expected to strongly affect the pH and concentration dependent self-assembly properties. The order of N to K(DO3A:M3+) is also not expected to strongly affect the pH and concentration dependent self-assembly properties.
n:o:q=16-17:1:2-3 with Carboxylic Acid Termination
PAs having a C16 (palmitoyl) or a C17 (heptadecanoyl) chain (n=16-17) and one B amino acid (n=1), but have an anionic carboxylic acid termination at the C-terminus need only 2-3 N amino acids (q=2-3). Also this transition can occur in the presence or absence of an ethyleneglycol-propionic acid tail with r=0-6. Example PAs that are expected to undergo this transition are shown in Table 8.
n:o:q=15-16:2:5-7 with Amide Termination
With two strongly β-sheet forming hydrophobic amino acids (o=2) and either a C15 (pentadecanoyl) or a C16 (palmitoyl) (n=15-16) the range of possible molecules that can undergo this transition in serum require 5-7 charged N residues (q=5-7) in the presence or absence of an ethyleneglycol-propionic amide tail with r=0-6. Example PAs that are expected to undergo this transition are shown in Table 9.
In contrast, numerous molecules were synthesized with two strongly hydrophobic amino acids that self-assemble as cylindrical nanofibers across all pH values in simulated serum solutions. In these sequences, the attractive supramolecular forces are too strong (Table 10).
Alternatively, in the sequences below, when the attractive forces are too weak either due to the shorter alkyl chain, or the weakness of these molecules assemble as single molecules at all pH values (Table 11).
n:o:q=15-16:2:4-6 with Acid Termination
With two strongly β-sheet forming hydrophobic amino acids (o=2), acid termination, and either a C15 (pentadecanoyl) or a C16 (palmitoyl) (n=15-16), the range of possible molecules that can undergo this transition in serum requires 4-6 charged N residues (q=4-6) in the presence or absence of an ethyleneglycol-propionic acid tail with r=0-6. Example PAs that are expected to undergo this transition in serum are shown in Table 12.
Unless defined otherwise, all technical and scientific terms used herein have the same meanings as commonly understood by one of skill in the art to which the disclosed invention belongs. Publications cited herein and the materials for which they are cited are specifically incorporated by reference.
Those skilled in the art will recognize, or be able to ascertain using no more than routine experimentation, many equivalents to the specific embodiments of the invention described herein. Such equivalents are intended to be encompassed by the following claims.
This application claims benefit of U.S. Provisional Application No. 61/593,581, filed Feb. 1, 2012, which is hereby incorporated herein by reference in its entirety.
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/US2013/024339 | 2/1/2013 | WO | 00 | 7/16/2014 |
| Number | Date | Country | |
|---|---|---|---|
| 61593581 | Feb 2012 | US |
