Patent Application
20200087451
The present disclosure relates generally to the fields of molecular and cellular biology, cancer imaging, nanotechnology, fluorescence sensors, and sensors for positron emission topography. More particularly, it relates to nanoplatforms for the detection of pH changes.
Cancer exhibits diverse genetic and histological differences from normal tissues (Vogelstein et al., 2013). Molecular characterization of these differences is useful to stratify patients towards personalized therapy. However, the strategy may not serve as a broad diagnostic tool because genetic/phenotypic biomarkers are expressed in a subset of patients and significant overlap with normal tissues exist (Jacobs et al., 2000 and Paik et al., 2000). Deregulated energetics is a hallmark of cancer that occurs across many types of cancer (Hanahan and Weinberg, 2011). Elevated glucose metabolism in cancer cells has long been associated with aerobic glycolysis, where cancer cells preferentially take up glucose and convert it into lactic acid (Heiden et al., 2009). More recent studies using 13C-labelled glucose in lung cancer patients further demonstrate accelerated oxidative phosphorylation in addition to glycolysis as a cancer cell mechanism for growth and proliferation (Hensley et al., 2016). The clinical significance of the glucose metabolism is manifested by the wide use of 18F-fluorodeoxyglucose (FDG) positron emission tomography (PET; Zhu et al., 2011) where FDG, a radiolabeled glucose analog, is selectively taken up by overexpressed glucose transporters and trapped inside the cancer cells after phosphorylation by hexokinase for PET detection (Som et al., 1980).
Despite broad clinical adoption, FDG has many well-described pitfalls (Cook et al., 2004, Purohit et al., 2014, Truong et al., 2014, Culverwell et al., 2011, Truong et al., 2005, Bhargava et al., 2011, Blodgett et al., 2011, and Fukui et al., 2005) including relatively high false negative rates depending on tumor size and variable levels of FDG uptake in tumors and normal tissues. High physiologic uptake of FDG typically occurs in the brain, heart, kidneys, and urinary tract, obscuring the tumor signal from areas adjacent to these tissues (Truong et al., 2014). In head and neck cancer, high FDG uptake in Waldeyer's ring (nasopharyngeal, palatine and lingual tonsils), salivary glands, striated muscle, brown fat, or inflammation/infection all contribute to false positive signals (Cohade et al., 2003 and Perkins et al., 2013). For tumors less than 1 cm, inadequate accumulation of FDG in tumors over the surrounding normal tissues often leads to false negatives (Cook et al., 2004, Purohit et al., 2014, Blodgett et al., 2011, and Gould et al., 2001). In addition, skull base tumors in the vicinity of highly metabolic brain parenchyma or oropharyngeal and nasopharyngeal cancers in FDG-avid tonsillar tissue may yield false negative diagnoses (Harvey et al., 2010, Schoder, 2013, Castaigne et al., 2006, and Schmalfuss, 2012). The variability of FDG uptake, overlap in retention, and temporal fluctuations in metabolism for both normal and tumor tissues significantly limits the accuracy of FDG PET in cancer detection.
Previously reported was an indocyanine green (ICG)-encoded ultra pH sensitive (UPS) nanoprobe for the broad detection of a wide range of solid cancers by near infrared fluorescence imaging (Zhao et al., 2016). This optical tracer exploits the phase transition of the polymers to quench and unquench the fluorescence of dyes conjugated to the hydrophobic portion of the polymers. This optical output is discrete, all on or off with no intermediate values, leading to the high specificity and sensitivity in tumor detection. However, it was unclear whether the phase transition behavior of the polymers could be harnessed to generate a response or output other than fluorescence.
Due to the unmet clinical need for the development of broad and cancer-specific strategies for cancer detection across different tumor types with improved sensitivity and specificity, new polymers that can generate pH responsive systems for the imaging of tumors are of value to the development of diagnostic and imaging protocols.
In some aspects, the present disclosure provides polymers of the formula:
wherein:
R1 is hydrogen, alkyl(C≤12), cycloalkyl(C≤12), substituted alkyl(C≤12), substituted cycloalkyl(C≤12), or
R3 and R11 are each independently a group of the formula:
wherein:
w is an integer from 0 to 150;
x is an integer from 1 to 150;
R4 is a group of the formula:
wherein:
y is an integer from 1-6;
R5 is a group of the formula:
wherein:
z is an integer from 1-6; and
R6 is hydrogen, halo, hydroxy, alkyl(C≤12), or substituted alkyl(C≤12),
wherein R11, R3, R4, and R5 can occur in any order within the polymer.
In some embodiments, the polymer is defined by the formula wherein:
R1 is hydrogen, alkyl(C≤12), substituted alkyl(C≤12), or
n is an integer from 10 to 500;
R2 and R2′ are each independently selected from hydrogen, alkyl(C≤12), or substituted alkyl(C≤12);
R3 and R11 are each independently a group of the formula:
wherein:
wherein:
y is an integer from 1 to 6;
R5 is a group of the formula:
wherein:
z is an integer from 1-6; and
R6 is hydrogen, halo, alkyl(C≤12), or substituted alkyl(C≤12),
wherein R11, R3, R4, and R5 can occur in any order within the polymer.
In some embodiments, the polymer is further defined by the formula wherein:
R1 is hydrogen, alkyl(C≤8), substituted alkyl(C≤8), or
n is an integer from 10 to 200;
R2 and R2′ are each independently selected from hydrogen, alkyl(C≤8), or substituted alkyl(C≤8);
R3 and R11 are each independently a group of the formula:
wherein:
wherein:
y is an integer from 1 to 6;
R5 is a group of the formula:
wherein:
z is an integer from 1-6; and
R6 is hydrogen, halo, alkyl(C≤6), or substituted alkyl(C≤6),
wherein R11, R3, R4, and R5 can occur in any order within the polymer.
In some embodiments, R1 is hydrogen. In other embodiments, R1 is alkyl(C≤6), such as methyl. In still other embodiments, R1 is
In some embodiments, R2 is alkyl(C≤6), such as methyl. In some embodiments, R2′ is alkyl(C≤6), such as methyl. In some embodiments, R3 or R11 is further defined by the formula:
wherein:
In some embodiments, X1 is alkyl(C≤6), such as methyl. In some embodiments, X4 is alkyl(C≤8), such as methyl, ethyl, propyl, butyl, or pentyl. In some embodiments, X4 is n-propyl. In other embodiments, X4 is isopropyl. In other embodiments, X4 is ethyl. In some embodiments, X5 is alkyl(C≤8), such as methyl, ethyl, propyl, butyl, or pentyl. In some embodiments, X5 is n-propyl. In other embodiments, X5 is isopropyl. In other embodiments, X5 is ethyl. In some embodiments, R3 and R11 are not same group.
In some embodiments, R4 is further defined by the formula:
wherein: Y1 is selected from hydrogen, alkyl(C≤8), or substituted alkyl(C≤8); and Y4 is a dye or a fluorescence quencher. In some embodiments, Y1 is alkyl(C≤6), such as methyl. In some embodiments, Y4 is a dye. In some embodiments, Y4 is fluorescent dye. In some embodiments, the fluorescent dye is a coumarin, fluorescein, rhodamine, xanthene, BODIPY®, Alexa Fluor®, or cyanine dye. In some embodiments, the fluorescent dye is indocyanine green, AMCA-x, Marina Blue, PyMPO, Rhodamine Green™, Tetramethylrhodamine, 5-carboxy-X-rhodamine, Bodipy493, Bodipy TMR-x, Bodipy630, Cyanine3.5, Cyanine5, Cyanine5.5, or Cyanine7.5. In some embodiments, the fluorescent dye is indocyanine green.
In some embodiments, Y4 is a fluorescence quencher, such as QSY7, QSY21, QSY35, BHQ1, BHQ2, BHQ3, TQ1, TQ2, TQ3, TQ4, TQ5, TQ6, or TQ7. In some embodiments, each Ru is incorporated consecutively to form a block. In some embodiments, each R3 is incorporated consecutively to form a block. In some embodiments, each R11 is present as a block and each R3 is present as a block. In other embodiments, each R11 and each R3 are randomly incorporated within the polymer.
In some embodiments, R5 is further defined by the formula:
wherein:
Y1′ is selected from hydrogen, alkyl(C≤8), substituted alkyl(C≤8);
Y4′ is a metal chelating group; and
L is a covalent bond; or
In some embodiments, Y1′ is alkyl(C≤6), such as methyl. In some embodiments, L is a covalent bond. In other embodiments, L is alkanediyl(C≤12), substituted alkanediyl(C≤12), arenediyl(C≤12), or substituted arenediyl(C≤12). In still other embodiments, L is -alkanediyl(C≤12), -arenediyl(C≤12)-NC(S)—. In further embodiments, L is -alkanediyl(C≤12)-benzenediyl-NC(S)—, such as —CH2-1,4-benzenediyl-NC(S)—. In some embodiments, Y4′ is DOTA, TETA, Diamsar, NOTA, NETA, TACN-TM, DTPA, TRAP, NOPO, AAZTA, DATA, HBED, SHBED, BPCA, CP256, DFO, PCTA, HEHA, PEPA, or a derivative thereof. In some embodiments, Y4′ is a metal chelating group wherein the metal chelating group is a nitrogen containing macrocycle. In further embodiments, the nitrogen containing macrocycle is a compound of the formula:
wherein:
In some embodiments, the metal chelating group is:
In some embodiments, the metal chelating group is bound to a metal ion to form a metal complex. In some embodiments, the metal ion is a radionuclide or radiometal. In some embodiments, the metal ion is suitable for PET or SPECT imaging. In some embodiments, the metal ion is a transition metal ion. In some embodiments, the metal ion is a copper ion, a gallium ion, a scandium ion, an indium ion, a lutetium ion, a ytterbium ion, a zirconium ion, a bismuth ion, a lead ion, a actinium ion, or a technetium ion. In some embodiments, the metal ion is an isotope selected from 99mTc, 60Cu, 61Cu, 62Cu, 64Cu, 86Y, 90Y, 89Zr, 44Sc, 47Sc, 66Ga, 67Ga, 68Ga, 111In, 177Lu, 225Ac, 212Pb, 212Bi, 213Bi, 111In, 114mIn, 114In, 186Re, or 188Re. In some embodiments, the transition metal ion is a copper(II) ion. In some embodiments, the copper(II) ion is a 64Cu2+ ion. In some embodiments, the metal complex is:
In some embodiments, n is 75-150. In further embodiments, n is 100-125. In some embodiments, x is 1-99. In further embodiments, x is from 1-5, 5-10, 10-15, 15-20, 20-25, 25-30, 30-35, 35-40, 40-45, 45-50, 50-55, 55-60, 60-65, 65-70, 70-75, 75-80, 80-85, 85-90, 90-95, 95-100, 100-105, 105-110, 110-115, 115-120, 120-125, 125-130, 130-135, 135-140, 140-145, 145-150, 150-155, 155-160, 160-165, 165-170, 170-175, 175-180, 180-185, 185-190, 190-195, 195-199 or any range derivable therein. In some embodiments, y is 1, 2, 3, 4, or 5. In some embodiments, y is 1 or 2. In some embodiments, y is 1. In some embodiments, z is 1, 2, 3, 4, or 5. In some embodiments, z is 1 or 2. In some embodiments, z is 2. In some embodiments, each R11, R3, R4, and R5 can occur in any order within the polymer. In other embodiments, each R11, R3, R4, and R5 occur in the order described in formula I. In some embodiments, w is 0.
In some embodiments, the polymer further comprises a targeting moiety. In further embodiments, targeting moiety is a small molecule, an antibody, an antibody fragment, or a signaling peptide. In some embodiments, R3 and R11 are selected from:
In some embodiments, R3 is:
In some embodiments, the polymer has a pH transition of 6.9. In some embodiments, the polymer is UPS6.9.
In another aspect, the present disclosure provides micelles of a polymer as disclosed herein.
In another aspect, the present disclosure provides pH responsive systems comprising a micelle of a first polymer wherein the first polymer is a polymer of the present disclosure, wherein Y4 is a dye, and wherein the micelle has a pH transition point and an emission spectrum. In some embodiments, the micelle further comprises a second polymer is a polymer as disclosed herein, wherein Y4 is a fluorescence quencher. In some embodiments, the second polymer has the same formula as the first polymer except that Y4 is a fluorescence quencher. In some embodiments, the micelle comprises a composition comprising a second polymer of the present disclosure, wherein the second polymer has a different formula than the first polymer. In some embodiments, Y4 on the second polymer is a different dye than the Y4 on the first polymer. In some embodiments, the micelle further comprises from 1 to 6 additional polymers provided that each polymer is unique that each polymer is different than the first polymer and the second polymer. In some embodiments, the pH transition point is between 3-9. In further embodiments, the pH transition point is between 4-8, such as 6.9. In some embodiments, the emission spectra is between 400-850 nm. In some embodiments, the system has a pH response (ΔpH10-90%) of less than 1 pH unit. In further embodiments, the pH response is less than 0.25 pH units. In still further embodiments, the pH response is less than 0.15 pH units. In some embodiments, the fluorescence signal has a fluorescence activation ratio of greater than 25. In further embodiments, the fluorescence activation ratio is greater than 50.
In another aspect, the present disclosure provides methods of imaging the pH of an intracellular or extracellular environment comprising:
In some embodiments, at least one of the one of more signals is positron emission. In some embodiments, at least one of the one of more signals is an optical signal, such as a fluorescent signal. In some embodiments, when the intracellular environment is imaged, the cell is contacted with the pH responsive system under conditions suitable to cause uptake of the pH responsive system. In some embodiments, the intracellular environment is part of a cell. In further embodiments, the part of the cell is lysosome or an endosome. In some embodiments, the extracellular environment is of a tumor or vascular cell. In some embodiments, the extracellular environment is intravascular or extravascular. In some embodiments, imaging the pH of the tumor environment comprises imaging the cancer-involved or sentinel lymph node or nodes. In further embodiments, imaging the cancer-involved or sentinel lymph node or nodes allows for the surgical resection of the tumor and staging of the tumor metastasis. In some embodiments, imaging the pH of the tumor environment allows determination of the tumor size and margins. In further embodiments, imaging the pH of the tumor environment allows for more precise removal of the tumor during surgery.
In some embodiments, the method further comprises:
In some embodiments, at least one of the one or more signals is an optical signal. In some embodiments, at least one of the one or more signals is positron emission. In some embodiments, the compound of interest is a drug, antibody, peptide, protein, nucleic acid, or small molecule.
In still another aspect, the present disclosure provides methods of delivering a compound of interest to a target cell comprising:
In some embodiments, the compound of interest is delivered into the cell. In other embodiments, the compound of interest is delivered to the cell. In some embodiments, the compound of interest is a drug, antibody, peptide, protein, nucleic acid, or small molecule. In some embodiments, the method further comprises administering the pH responsive system to a patient.
In yet another aspect, the present disclosure provides methods of resecting a tumor in a patient comprising:
In some embodiments, at least one of the one or more signals is an optical signal. In some embodiments, at least one of the one or more signals is positron emission. In some embodiments, the one or more signals indicate the margins of the tumor. In some embodiments, the tumor is 90% resected. In further embodiments, the tumor is 95% resected. In still further embodiments, the tumor is 99% resected. In some embodiments, the tumor is a solid tumor. In some embodiments, the solid tumor is from a cancer. In some embodiments, the cancer is a breast cancer, a head and neck cancer, or a brain cancer. In some embodiments, the cancer is head and neck squamous cell carcinoma. In some embodiments, the pH responsive system is comprised of a polymer of the formula:
wherein: x is an integer from 30 to 150, y is 1 or 2, z is 1 or 2; x, y, and z are randomly distributed throughout the polymer; ICG is the fluorescent dye indocyanine green.
In yet another aspect, the present disclosure provides methods of treating a cancer susceptible to endosomal/lysosomal pH arrest in a patient comprising administering to the patient in need thereof a pH responsive system of the present disclosure. In some embodiments, the cancer is a lung cancer, such as a non-small cell lung cancer. In some embodiments, the method is sufficient to induce apoptosis.
In still another aspect, the present disclosure provides methods of identifying the tumor acidosis pathway comprising:
In some embodiments, the signal is an optical signal, such as fluorescence. In some embodiments, the signal is positron emission. In some embodiments, the inhibitor of the pH regulatory pathway is an inhibitor of a monocarboxylate transporter, a carbonic anhydrase, an anion exchanger, a Nat-bicarbonate exchanger, a Na+/H+ exchanger, or a V-ATPase. In some embodiments, the one or more micelles comprise a polymer with two or more fluorophores attached to the polymer backbone. In further embodiments, the method comprises one micelle and the micelle comprises two or more polymers with different fluorophores or different R3 groups. In some embodiments, the micelle comprises two or more polymers with different fluorophores and different R3 groups.
In still another aspect, the present disclosure provides methods of imaging a patient to determine the presence of a tumor comprising:
wherein: R7, R8, R9, R10, R7′, R8′, R9′ a, b, c, d, a′, b′, and c′ are as defined above. In some embodiments, the nitrogen containing macrocycle is:
In some aspects, the present disclosure provides methods of determining the efficacy of a cancer treatment therapy comprising:
In some embodiments, the cancer treatment therapy is chemotherapy or radiation therapy. In some embodiments, chemotherapy comprises administration of a chemotherapeutic agent that modulates the tumor acidosis pathway.
In yet another aspect, the present disclosure provides methods of treating or preventing a disease or disorder in a patient in need thereof comprising administering to the patient a polymer, micelle, or pH responsive system described herein. In some embodiments, the polymer, micelle, or pH responsive system comprises a radionuclide, such as 90Y or 177Lu. In some embodiments, the polymer, micelle, or pH responsive system further comprises a second therapeutic agent.
As used herein, “pH responsive system,” “micelle,” “pH-responsive micelle,” “pH-sensitive micelle,” “pH-activatable micelle” and “pH-activatable micellar (pHAM) nanoparticle” are used interchangeably herein to indicate a micelle comprising one or more block copolymers, which disassociates depending on the pH (e.g., above or below a certain pH). As a non-limiting example, at a certain pH, the block copolymer is substantially in micellar form. As the pH changes (e.g., decreases), the micelles begin to disassociate, and as the pH further changes (e.g., further decreases), the block copolymer is present substantially in disassociated (non-micellar) form.
As used herein, “pH transition range” indicates the pH range over which the micelles disassociate.
As used herein, “pH transition value” (pHt) indicates the pH at which half of the micelles are disassociated.
It is contemplated that any method or composition described herein can be implemented with respect to any other method or composition described herein.
The terms “comprise” (and any form of comprise, such as “comprises” and “comprising”), “have” (and any form of have, such as “has” and “having”), “contain” (and any form of contain, such as “contains” and “containing”), and “include” (and any form of include, such as “includes” and “including”) are open-ended linking verbs. As a result, a method, composition, kit, or system that “comprises,” “has,” “contains,” or “includes” one or more recited steps or elements possesses those recited steps or elements but is not limited to possessing only those steps or elements; it may possess (i.e., cover) elements or steps that are not recited. Likewise, an element of a method, composition, kit, or system that “comprises,” “has,” “contains,” or “includes” one or more recited features possesses those features but is not limited to possessing only those features; it may possess features that are not recited.
Any embodiment of any of the present methods, composition, kit, and systems may consist of or consist essentially of—rather than comprise/include/contain/have—the described steps and/or features. Thus, in any of the claims, the term “consisting of” or “consisting essentially of” may be substituted for any of the open-ended linking verbs recited above, in order to change the scope of a given claim from what it would otherwise be using the open-ended linking verb.
The polymers of the present disclosure may be depicted in various protonation states. As would be recognized by a skilled artisan, molecules exist in different protonation states at different pH values. The depiction of a molecule in one protonation state does not mean that that molecule solely exists in that protonation state at that pH value or another pH value. Thus, the present polymers are contemplated to encompass all feasible protonation states. For example, an amine may be represented as either protonated or unprotonated or a carboxylic acid group may be depicted as either as the free acid or a carboxylate.
The use of the term “or” in the claims is used to mean “and/or” unless explicitly indicated to refer to alternatives only or the alternatives are mutually exclusive, although the disclosure supports a definition that refers to only alternatives and “and/or.” Throughout this application, the term “about” is used to indicate that a value includes the standard deviation of error for the device or method being employed to determine the value. Following long-standing patent law, the words “a” and “an,” when used in conjunction with the word “comprising” in the claims or specification, denotes one or more, unless specifically noted.
Other objects, features and advantages of the present disclosure will become apparent from the following detailed description. It should be understood, however, that the detailed description and the specific examples, while indicating specific embodiments of the disclosure, are given by way of illustration only, since various changes and modifications within the spirit and scope of the disclosure will become apparent to those skilled in the art from this detailed description.
The patent or application file contains at least one drawing executed in color. Copies of this patent or patent application publication with color drawing(s) will be provided by the Office upon request and payment of the necessary fee.
The following drawings form part of the present specification and are included to further demonstrate certain aspects of the present disclosure. The disclosure may be better understood by reference to one or more of these drawings in combination with the detailed description of specific embodiments presented herein.
In some aspects, the present disclosure provides a polymer which can form a pH responsive nanoparticle which dissembles above a particular transition pH. In some embodiments, these polymers comprise a mixture of different monomers which allow specific tailoring of the desired pH transition point (ΔpH10-90%) of less than 0.2 pH units as well as develop pH probes for a range of pH transition points from about a pH of 4 to about a pH of 8. The wide range of pH transition points allows for a wide range of application including but not limited to vesicular trafficking, imaging of the pHe of tumors, delivering drug compounds to specific tissues, improving the visualization of a tumor to improve the ability of a surgeon to resect the tumor tissue, or study the maturation or development of endosomes/lysosomes. In some aspects, the polymers of the present disclosure comprise a metal chelating group and a dye or fluorescence quencher. In some aspects, the metal chelating group is chelated to a radionuclide, such as a radionuclide that emits positrons. In some aspects, the present disclosure provides methods of using these polymers in a pH responsive system as described above. Additional methods of using the polymers and the resultant pH responsive systems of the present disclosure are described in WO 2013/152059 and WO 2015/188157, which are incorporated herein by reference. In some embodiments, the compounds of the present invention have the advantage that they may be more efficacious than, be less toxic than, be longer acting than, be more potent than, produce fewer side effects than, be more easily absorbed than, more metabolically stable than, more lipophilic than, more hydrophilic than, and/or have a better pharmacokinetic profile (e.g., higher oral bioavailability and/or lower clearance) than, and/or have other useful pharmacological, physical, or chemical properties over, compounds known in the prior art, whether for use in the indications stated herein or otherwise.
When used in the context of a chemical group: “hydrogen” means —H; “hydroxy” means —OH; “carboxy” means —C(═O)OH (also written as —COOH or —CO2H); “halo” means independently —F, —Cl, —Br or —I; “amino” means —NH2; “nitro” means —NO2; “cyano” means —CN; in a monovalent context “phosphate” means —OP(O)(OH)2 or a deprotonated form thereof; in a divalent context “phosphate” means —OP(O)(OH)O— or a deprotonated form thereof; “mercapto” means —SH; and “thio” means=S; “sulfonyl” means —S(O)2—; and “sulfinyl” means —S(O)—.
In the context of chemical formulas, the symbol “-” means a single bond, “=” means a double bond, and “≡” means triple bond. The symbol “----” represents an optional bond, which if present is either single or double. The symbol “” represents a single bond or a double bond. Thus, for example, the formula
includes
And it is understood that no one such ring atom forms part of more than one double bond. Furthermore, it is noted that the covalent bond symbol “-”, when connecting one or two stereogenic atoms, does not indicate any preferred stereochemistry. Instead, it covers all stereoisomers as well as mixtures thereof. The symbol “”, when drawn perpendicularly across a bond (e.g.,
for methyl) indicates a point of attachment of the group. It is noted that the point of attachment is typically only identified in this manner for larger groups in order to assist the reader in unambiguously identifying a point of attachment. The symbol “” means a single bond where the group attached to the thick end of the wedge is “out of the page.” The symbol “
” means a single bond where the group attached to the thick end of the wedge is “into the page”. The symbol “
” means a single bond where the geometry around a double bond (e.g., either E or Z) is undefined. Both options, as well as combinations thereof are therefore intended. Any undefined valency on an atom of a structure shown in this application implicitly represents a hydrogen atom bonded to that atom. A bold dot on a carbon atom indicates that the hydrogen attached to that carbon is oriented out of the plane of the paper.
When a group “R” is depicted as a “floating group” on a ring system, for example, in the formula:
then R may replace any hydrogen atom attached to any of the ring atoms, including a depicted, implied, or expressly defined hydrogen, so long as a stable structure is formed. When a group “R” is depicted as a “floating group” on a fused ring system, as for example in the formula:
then R may replace any hydrogen attached to any of the ring atoms of either of the fused rings unless specified otherwise. Replaceable hydrogens include depicted hydrogens (e.g., the hydrogen attached to the nitrogen in the formula above), implied hydrogens (e.g., a hydrogen of the formula above that is not shown but understood to be present), expressly defined hydrogens, and optional hydrogens whose presence depends on the identity of a ring atom (e.g., a hydrogen attached to group X, when X equals —CH—), so long as a stable structure is formed. In the example depicted, R may reside on either the 5-membered or the 6-membered ring of the fused ring system. In the formula above, the subscript letter “y” immediately following the group “R” enclosed in parentheses, represents a numeric variable. Unless specified otherwise, this variable can be 0, 1, 2, or any integer greater than 2, only limited by the maximum number of replaceable hydrogen atoms of the ring or ring system.
For the groups and classes below, the following parenthetical subscripts further define the group/class as follows: “(Cn)” defines the exact number (n) of carbon atoms in the group/class. “(C≤n)” defines the maximum number (n) of carbon atoms that can be in the group/class, with the minimum number as small as possible for the group in question, e.g., it is understood that the minimum number of carbon atoms in the group “alkenyl(C≤8)” or the class “alkene(C≤8)” is two. For example, “alkoxy(C≤10)” designates those alkoxy groups having from 1 to 10 carbon atoms. (Cn-n′) defines both the minimum (n) and maximum number (n′) of carbon atoms in the group. Similarly, “alkyl(C2-10)” designates those alkyl groups having from 2 to 10 carbon atoms.
The term “saturated” as used herein means the compound or group so modified has no carbon-carbon double and no carbon-carbon triple bonds, except as noted below. In the case of substituted versions of saturated groups, one or more carbon oxygen double bond or a carbon nitrogen double bond may be present. And when such a bond is present, then carbon-carbon double bonds that may occur as part of keto-enol tautomerism or imine/enamine tautomerism are not precluded.
The term “aliphatic” when used without the “substituted” modifier signifies that the compound/group so modified is an acyclic or cyclic, but non-aromatic hydrocarbon compound or group. In aliphatic compounds/groups, the carbon atoms can be joined together in straight chains, branched chains, or non-aromatic rings (alicyclic). Aliphatic compounds/groups can be saturated, that is joined by single bonds (alkanes/alkyl), or unsaturated, with one or more double bonds (alkenes/alkenyl) or with one or more triple bonds (alkynes/alkynyl).
The term “alkyl” when used without the “substituted” modifier refers to a monovalent saturated aliphatic group with a carbon atom as the point of attachment, a linear or branched acyclic structure, and no atoms other than carbon and hydrogen. The groups —CH3 (Me), —CH2CH3 (Et), —CH2CH2CH3 (n-Pr or propyl), —CH(CH3)2 (i-Pr, iPr or isopropyl), —CH2CH2CH2CH3 (n-Bu), —CH(CH3)CH2CH3 (sec-butyl), —CH2CH(CH3)2 (isobutyl), —C(CH3)3 (tert-butyl, t-butyl, t-Bu or tBu), and —CH2C(CH3)3 (neo-pentyl) are non-limiting examples of alkyl groups. The term “alkanediyl” when used without the “substituted” modifier refers to a divalent saturated aliphatic group, with one or two saturated carbon atom(s) as the point(s) of attachment, a linear or branched acyclic structure, no carbon-carbon double or triple bonds, and no atoms other than carbon and hydrogen. The groups, —CH2— (methylene), —CH2CH2—, —CH2C(CH3)2CH2—, and —CH2CH2CH2—, are non-limiting examples of alkanediyl groups. The term “alkylidene” when used without the “substituted” modifier refers to the divalent group ═CRR′ in which R and R′ are independently hydrogen or alkyl. Non-limiting examples of alkylidene groups include: ═CH2, ═CH(CH2CH3), and ═C(CH3)2. An “alkane” refers to the compound H—R, wherein R is alkyl as this term is defined above. When any of these terms is used with the “substituted” modifier one or more hydrogen atom has been independently replaced by —OH, —F, —Cl, —Br, —I, —NH2, —NO2, —CO2H, —CO2CH3, —CN, —SH, —OCH3, —OCH2CH3, —C(O)CH3, —NHCH3, —NHCH2CH3, —N(CH3)2, —C(O)NH2, —OC(O)CH3, or —S(O)2NH2. The following groups are non-limiting examples of substituted alkyl groups: —CH2OH, —CH2Cl, —CF3, —CH2CN, —CH2C(O)OH, —CH2C(O)OCH3, —CH2C(O)NH2, —CH2C(O)CH3, —CH2OCH3, —CH2OC(O)CH3, —CH2NH2, —CH2N(CH3)2, and —CH2CH2Cl. The term “haloalkyl” is a subset of substituted alkyl, in which one or more hydrogen atoms has been substituted with a halo group and no other atoms aside from carbon, hydrogen and halogen are present. The group, —CH2Cl is a non-limiting example of a haloalkyl. The term “fluoroalkyl” is a subset of substituted alkyl, in which one or more hydrogen has been substituted with a fluoro group and no other atoms aside from carbon, hydrogen and fluorine are present. The groups, —CH2F, —CF3, and —CH2CF3 are non-limiting examples of fluoroalkyl groups.
The term “cycloalkyl” when used without the “substituted” modifier refers to a monovalent saturated aliphatic group with a carbon atom as the point of attachment, a linear or branched cyclo or cyclic structure, no carbon-carbon double or triple bonds, and no atoms other than carbon and hydrogen. As used herein, the cycloalkyl group may contain one or more branching alkyl groups (carbon number limit permitting) attached to the ring system so long as the point of attachment is the ring system. Non-limiting examples of cycloalkyl groups include: —CH(CH2)2 (cyclopropyl), cyclobutyl, cyclopentyl, or cyclohexyl. The term “cycloalkanediyl” when used without the “substituted” modifier refers to a divalent saturated aliphatic group with one or two carbon atom as the point(s) of attachment, a linear or branched cyclo or cyclic structure, no carbon-carbon double or triple bonds, and no atoms other than carbon and hydrogen.
are non-limiting examples of cycloalkanediyl groups. The term “cycloalkylidene” when used without the “substituted” modifier refers to the divalent group ═CRR′ in which R and R′ are taken together to form a cycloalkanediyl group with at least two carbons. Non-limiting examples of alkylidene groups include: ═C(CH2)2 and ═C(CH2)5. A “cycloalkane” refers to the compound H—R, wherein R is cycloalkyl as this term is defined above. When any of these terms is used with the “substituted” modifier one or more hydrogen atom has been independently replaced by —OH, —F, —Cl, —Br, —I, —NH2, —NO2, —CO2H, —CO2CH3, —CN, —SH, —OCH3, —OCH2CH3, —C(O)CH3, —NHCH3, —NHCH2CH3, —N(CH3)2, —C(O)NH2, —OC(O)CH3, or —S(O)2NH2. The following groups are non-limiting examples of substituted cycloalkyl groups: —C(OH)(CH2)2,
The term “aryl” when used without the “substituted” modifier refers to a monovalent unsaturated aromatic group with an aromatic carbon atom as the point of attachment, said carbon atom forming part of a one or more six-membered aromatic ring structure, wherein the ring atoms are all carbon, and wherein the group consists of no atoms other than carbon and hydrogen. If more than one ring is present, the rings may be fused or unfused. As used herein, the term does not preclude the presence of one or more alkyl or aralkyl groups (carbon number limitation permitting) attached to the first aromatic ring or any additional aromatic ring present. Non-limiting examples of aryl groups include phenyl (Ph), methylphenyl, (dimethyl)phenyl, —C6H4CH2CH3 (ethylphenyl), naphthyl, and a monovalent group derived from biphenyl. The term “arenediyl” when used without the “substituted” modifier refers to a divalent aromatic group with two aromatic carbon atoms as points of attachment, said carbon atoms forming part of one or more six-membered aromatic ring structure(s) wherein the ring atoms are all carbon, and wherein the monovalent group consists of no atoms other than carbon and hydrogen. As used herein, the term does not preclude the presence of one or more alkyl, aryl or aralkyl groups (carbon number limitation permitting) attached to the first aromatic ring or any additional aromatic ring present. If more than one ring is present, the rings may be fused or unfused. Unfused rings may be connected via one or more of the following: a covalent bond, alkanediyl, or alkenediyl groups (carbon number limitation permitting). Non-limiting examples of arenediyl groups include:
An “arene” refers to the compound H—R, wherein R is aryl as that term is defined above. Benzene and toluene are non-limiting examples of arenes. When any of these terms are used with the “substituted” modifier one or more hydrogen atom has been independently replaced by —OH, —F, —Cl, —Br, —I, —NH2, —NO2, —CO2H, —CO2CH3, —CN, —SH, —OCH3, —OCH2CH3, —C(O)CH3, —NHCH3, —NHCH2CH3, —N(CH3)2, —C(O)NH2, —OC(O)CH3, or —S(O)2NH2.
The term “heteroaryl” when used without the “substituted” modifier refers to a monovalent aromatic group with an aromatic carbon atom or nitrogen atom as the point of attachment, said carbon atom or nitrogen atom forming part of one or more aromatic ring structures wherein at least one of the ring atoms is nitrogen, oxygen or sulfur, and wherein the heteroaryl group consists of no atoms other than carbon, hydrogen, aromatic nitrogen, aromatic oxygen and aromatic sulfur. If more than one ring is present, the rings may be fused or unfused. As used herein, the term does not preclude the presence of one or more alkyl, aryl, and/or aralkyl groups (carbon number limitation permitting) attached to the aromatic ring or aromatic ring system. Non-limiting examples of heteroaryl groups include furanyl, imidazolyl, indolyl, indazolyl (Im), isoxazolyl, methylpyridinyl, oxazolyl, phenylpyridinyl, pyridinyl, pyrrolyl, pyrimidinyl, pyrazinyl, quinolyl, quinazolyl, quinoxalinyl, triazinyl, tetrazolyl, thiazolyl, thienyl, and triazolyl. The term “N-heteroaryl” refers to a heteroaryl group with a nitrogen atom as the point of attachment. The term “heteroarenediyl” when used without the “substituted” modifier refers to an divalent aromatic group, with two aromatic carbon atoms, two aromatic nitrogen atoms, or one aromatic carbon atom and one aromatic nitrogen atom as the two points of attachment, said atoms forming part of one or more aromatic ring structure(s) wherein at least one of the ring atoms is nitrogen, oxygen or sulfur, and wherein the divalent group consists of no atoms other than carbon, hydrogen, aromatic nitrogen, aromatic oxygen and aromatic sulfur. If more than one ring is present, the rings may be fused or unfused. Unfused rings may be connected via one or more of the following: a covalent bond, alkanediyl, or alkenediyl groups (carbon number limitation permitting). As used herein, the term does not preclude the presence of one or more alkyl, aryl, and/or aralkyl groups (carbon number limitation permitting) attached to the aromatic ring or aromatic ring system. Non-limiting examples of heteroarenediyl groups include:
A “heteroarene” refers to the compound H—R, wherein R is heteroaryl. Pyridine and quinoline are non-limiting examples of heteroarenes. When these terms are used with the “substituted” modifier one or more hydrogen atom has been independently replaced by —OH, —F, —Cl, —Br, —I, —NH2, —NO2, —CO2H, —CO2CH3, —CN, —SH, —OCH3, —OCH2CH3, —C(O)CH3, —NHCH3, —NHCH2CH3, —N(CH3)2, —C(O)NH2, —OC(O)CH3, or —S(O)2NH2.
The term “acyl” when used without the “substituted” modifier refers to the group —C(O)R, in which R is a hydrogen, alkyl, cycloalkyl, aryl, aralkyl or heteroaryl, as those terms are defined above. The groups, —CHO, —C(O)CH3 (acetyl, Ac), —C(O)CH2CH3, —C(O)CH2CH2CH3, —C(O)CH(CH3)2, —C(O)CH(CH2)2, —C(O)C6H5, —C(O)C6H4CH3, —C(O)CH2C6H5, —C(O)(imidazolyl) are non-limiting examples of acyl groups. A “thioacyl” is defined in an analogous manner, except that the oxygen atom of the group —C(O)R has been replaced with a sulfur atom, —C(S)R. The term “aldehyde” corresponds to an alkane, as defined above, wherein at least one of the hydrogen atoms has been replaced with a —CHO group. When any of these terms are used with the “substituted” modifier one or more hydrogen atom (including a hydrogen atom directly attached the carbonyl or thiocarbonyl group, if any) has been independently replaced by —OH, —F, —Cl, —Br, —I, —NH2, —NO2, —CO2H, —CO2CH3, —CN, —SH, —OCH3, —OCH2CH3, —C(O)CH3, —NHCH3, —NHCH2CH3, —N(CH3)2, —C(O)NH2, —OC(O)CH3, or —S(O)2NH2. The groups, —C(O)CH2CF3, —CO2H (carboxyl), —CO2CH3 (methylcarboxyl), —CO2CH2CH3, —C(O)NH2 (carbamoyl), and —CON(CH3)2, are non-limiting examples of substituted acyl groups.
The term “alkoxy” when used without the “substituted” modifier refers to the group —OR, in which R is an alkyl, as that term is defined above. Non-limiting examples of alkoxy groups include: —OCH3 (methoxy), —OCH2CH3 (ethoxy), —OCH2CH2CH3, —OCH(CH3)2 (isopropoxy), and —OC(CH3)3 (tert-butoxy). The terms “cycloalkoxy”, “alkenyloxy”, “cycloalkenyloxy”, “alkynyloxy”, “aryloxy”, “aralkoxy”, “heteroaryloxy”, “heterocycloalkoxy”, and “acyloxy”, when used without the “substituted” modifier, refers to groups, defined as —OR, in which R is cycloalkyl, alkenyl, cycloalkenyl, alkynyl, aryl, aralkyl, heteroaryl, heterocycloalkyl, and acyl, respectively. The term “alkoxydiyl” refers to the divalent group —O-alkanediyl-, —O-alkanediyl-O—, or -alkanediyl-O-alkanediyl-. The terms “alkylthio”, “cycloalkylthio”, and “acylthio” when used without the “substituted” modifier refers to the group —SR, in which R is an alkyl, cycloalkyl, and acyl, respectively. The term “alcohol” corresponds to an alkane, as defined above, wherein at least one of the hydrogen atoms has been replaced with a hydroxy group. The term “ether” corresponds to an alkane, as defined above, wherein at least one of the hydrogen atoms has been replaced with an alkoxy or cycloalkoxy group. When any of these terms is used with the “substituted” modifier one or more hydrogen atom has been independently replaced by —OH, —F, —Cl, —Br, —I, —NH2, —NO2, —CO2H, —CO2CH3, —CN, —SH, —OCH3, —OCH2CH3, —C(O)CH3, —NHCH3, —NHCH2CH3, —N(CH3)2, —C(O)NH2, —OC(O)CH3, or —S(O)2NH2.
The term “alkylamino” when used without the “substituted” modifier refers to the group —NHR, in which R is an alkyl, as that term is defined above. Non-limiting examples of alkylamino groups include: —NHCH3 and —NHCH2CH3. The term “dialkylamino” when used without the “substituted” modifier refers to the group —NRR′, in which R and R′ can each independently be the same or different alkyl groups, or R and R′ can be taken together to represent an alkanediyl. Non-limiting examples of dialkylamino groups include: —N(CH3)2, —N(CH3)(CH2CH3), and N-pyrrolidinyl. The terms “alkoxyamino”, “cycloalkylamino”, “alkenylamino”, “cycloalkenylamino”, “alkynylamino”, “arylamino”, “aralkylamino”, “heteroarylamino”, “heterocycloalkylamino” and “alkylsulfonylamino” when used without the “substituted” modifier, refers to groups, defined as —NHR, in which R is alkoxy, cycloalkyl, alkenyl, cycloalkenyl, alkynyl, aryl, aralkyl, heteroaryl, heterocycloalkyl, and alkylsulfonyl, respectively. A non-limiting example of an arylamino group is —NHC6H5. The term “amido” (acylamino), when used without the “substituted” modifier, refers to the group —NHR, in which R is acyl, as that term is defined above. A non-limiting example of an amido group is —NHC(O)CH3. The term “alkylimino” when used without the “substituted” modifier refers to the divalent group ═NR, in which R is an alkyl, as that term is defined above. The term “alkylaminodiyl” refers to the divalent group —NH— alkanediyl-, —NH— alkanediyl-NH—, or -alkanediyl-NH-alkanediyl-. When any of these terms is used with the “substituted” modifier one or more hydrogen atom has been independently replaced by —OH, —F, —Cl, —Br, —I, —NH2, —NO2, —CO2H, —CO2CH3, —CN, —SH, —OCH3, —OCH2CH3, —C(O)CH3, —NHCH3, —NHCH2CH3, —N(CH3)2, —C(O)NH2, —OC(O)CH3, or —S(O)2NH2. The groups —NHC(O)OCH3 and —NHC(O)NHCH3 are non-limiting examples of substituted amido groups.
The present disclosure also relates to imaging the extracellular pH (pHe) of a cell or group of cells. In particular, the extracellular environment could be of a tumor cell. Aerobic glycolysis (a.k.a., Warburg effect), where cancer cells preferentially take up glucose and convert it into lactic acids, has rekindled intense interest in imaging pHe of a tumor cell as a method of determine the presence of tumor tissue (Heiden et al., 2009). The clinical relevance of the Warburg effect has already been manifested by the wide clinical use of 2-18F-deoxyglucose (FDG) for tumor diagnosis as well as monitoring treatment responses. In tumor microenvironment, lactic acids are preferentially accumulated in the extracellular space due to monocarboxylate transporters, which are elevated in cancer cell membranes (Halestrap & Prince 1999). The resulting acidification of extracellular pH (pHe) in tumors promotes remodeling of extracellular matrix for increased tumor invasion and metastasis. Recently, Barber and coworkers described dysregulated pH in tumors as another “hallmark of cancer” (Webb et al., 2011).
Many previous studies have been performed to quantify the pHe in the tumor microenvironment (Gillies et al., 1994; Gillies et al., 2004; van Sluis et al., 1999 and Volk et al., 1993), including a representative pHe study in 268 tumors from 30 different human cancer cell lines (Volk et al., 1993). Compared to blood pH (7.4), all the tumor pHe are acidic with an average of 6.84 ranging from 6.71 to 7.01. Although the acidity of tumor pHe is persistent, exploiting it for tumor-specific imaging is challenging due to the relatively small pH differences (i.e., <1 pH unit) making probes which possess a very narrow pH transition range of particular interest for this application.
In some embodiments, the present disclosure provides polymers and micelles which can be used in a pH responsive system that can image and physiological and/or pathological process that is affected or affects intracellular or extracellular pH including but not limited to infections, fistulas, ulcers, ketoacidosis from diabetes or other diseases, hypoxia, metabolic acidosis, respiratory acidosis, toxic ingestion, poisoning, bone turnover, degenerative diseases, wounds, and tissue damage from burns radiation or other sources.
Positive tumor margins, which are defined by the presence of cancer cells at the edge of surgical resection, are the most important indicator of tumor recurrence and survival of HNSCC patients after surgery (Woolgar & Triantafyllou 2005; McMahon et al., 2003; Ravasz et al., Atkins et al., 2012 and Iczkowski & Lucia 2011). In some embodiments, any cancer cell line which exhibits a different extracellular pH environment than the normal physiological pH of the environment can be imaged with a pH responsive system disclosed herein. Furthermore, by modifying the dye used in the pH responsive dyes, a variety of different commercially available surgical imaging systems can be used to measure the margins of the tumor. These systems include but are not limited to systems for open surgery (e.g., SPY Elite®), microsurgery (Carl Zeiss, Leica), laparoscopy (Olympus, Karl Storz), and robotic surgery (da Vinci®). Many of these clinical systems have fast acquisition times allowing real-time imaging during an operation. Furthermore, the mixed polymers disclosed herein as well as a homopolymer of the any of the individual monomers used to create the mixed polymers can be used in the pH responsive system for the imaging of a tumor during an operation.
The pH-responsive micelles and nanoparticles disclosed herein comprise block copolymers and fluorescent dyes. A block copolymer comprises a hydrophilic polymer segment and a hydrophobic polymer segment. The hydrophobic polymer segment is pH sensitive. For example, the hydrophobic polymer segment may comprise an ionizable amine group to render pH sensitivity. The block copolymers form pH-activatable micellar (pHAM) nanoparticles based on the supramolecular self-assembly of these ionizable block copolymers. At higher pH, the block copolymers assemble into micelles, whereas at lower pH, ionization of the amine group in the hydrophobic polymer segment results in dissociation of the micelle. The ionizable groups may act as tunable hydrophilic/hydrophobic blocks at different pH values, which may directly affect the dynamic self-assembly of micelles.
For diagnostic or pH monitoring applications, a labeling moiety may be conjugated to the block copolymer. In some embodiments, the label (e.g., a fluorescent label) is sequestered inside the micelle when the pH favors micelle formation. Sequestration in the micelle results in a decrease in label signal (e.g., via fluorescence quenching). Specific pH conditions may lead to rapid protonation and dissociation of micelles into unimers, thereby exposing the label, and increasing the label signal (e.g., increasing fluorescence emission). The micelles of the disclosure may provide one or more advantages in diagnostic applications, such as: (1) disassociation of the micelle (and rapid increase in label signal) within a short amount of time (e.g., within minutes) under certain pH environments (e.g., acidic environments), as opposed to hours or days for previous micelle compositions; (2) increased imaging payloads; (3) selective targeting of label to the desired site (e.g., tumor or particular endocytic compartment); (4) prolonged blood circulation times; (5) responsiveness within specific narrow pH ranges (e.g., for targeting of specific organelles); and (6) high contrast sensitivity and specificity. For example, the micelles may stay silent (or in the OFF state) with minimum background signals under normal physiological conditions (e.g., blood circulation, cell culture conditions), but imaging signals can be greatly amplified when the micelles reach their intended molecular targets (e.g., extracellular tumor environment or cellular organelle).
Numerous fluorescent dyes are known in the art. In certain aspects of the disclosure, the fluorescent dye is a pH-insensitive fluorescent dyes. In some embodiments, the fluorescent dye is paired with a fluorescent quencher to obtain an increased signal change upon activation. The fluorescent dye may be conjugated to the copolymer directly or through a linker moiety. Methods known in the art may be used to conjugate the fluorescent dye to, for example, the hydrophobic polymer. In some embodiments, the fluorescent dye may be conjugated to amine of the hydrophobic polymer through an amide bond.
Examples of block copolymers and block copolymers conjugated to fluorescent dyes and metal chelating groups include:
wherein: R1 is hydrogen, alkyl(C≤12), cycloalkyl(C≤12), substituted alkyl(C≤12), substituted cycloalkyl(C≤12), or
n is an integer from 1 to 500; R2 and R2′ are each independently selected from hydrogen, alkyl(C≤12), cycloalkyl(C≤12), substituted alkyl(C≤12), or substituted cycloalkyl(C≤12); R3 and R11 are each independently a group of the formula:
wherein: nx is 1-10; X1, X2, and X3 are each independently selected from hydrogen, alkyl(C≤12), cycloalkyl(C≤12), substituted alkyl(C≤12), or substituted cycloalkyl(C≤12); and X4 and X5 are each independently selected from alkyl(C≤12), cycloalkyl(C≤12), aryl(C≤12), heteroaryl(C≤12) or a substituted version of any of these groups, or X4 and X5 are taken together and are alkanediyl(C≤12), alkoxydiyl(c≤12), alkylaminodiyl(C≤12), or a substituted version of any of these groups; w is an integer from 0 to 150; x is an integer from 1 to 150; R4 is a group of the formula:
wherein: ny is 1-10; Y1, Y2, and Y3 are each independently selected from hydrogen, alkyl(C≤12), cycloalkyl(C≤12), substituted alkyl(C≤12), or substituted cycloalkyl(C≤12); and Y4 is a dye or a fluorescence quencher; y is an integer from 1-6; R5 is a group of the formula:
wherein: nz is 1-10; Y1′, Y2′, and Y3′ are each independently selected from hydrogen, alkyl(C≤12), cycloalkyl(C≤12), substituted alkyl(C≤12), or substituted cycloalkyl(C≤12); and Y4′ is a metal chelating group; L is a covalent bond; or alkanediyl(C≤12), arenediyl(C≤12), alkanediyl(C≤12), -arenediyl(C≤12)-NC(S)—, -alkanediyl(C≤12), -arenediyl(C≤12)-C(O)—, or a substituted version of any of these groups; z is an integer from 1-6; and R6 is hydrogen, halo, hydroxy, alkyl(C≤12), or substituted alkyl(C≤12), wherein R11, R3, R4, and R5 can occur in any order within the polymer. In some embodiments, each monomer of R11, R3, R4, and R5 within the longer polymer can occur in any order within the polymer. In some embodiments, the specific composition of the polymer (molar fraction of each R3, R4, and R5 monomers) is related to the specific pH transition point of the nanoparticle produced using that polymer.
The systems and compositions disclosed herein utilize either a single micelle or a series of micelles tuned to different pH levels. Furthermore, the micelles have a narrow pH transition range. In some embodiments, the micelles have a pH transition range of less than about 1 pH unit. In various embodiments, the micelles have a pH transition range of less than about 0.9, less than about 0.8, less than about 0.7, less than about 0.6, less than about 0.5, less than about 0.4, less than about 0.3, less than about 0.25, less than about 0.2, or less than about 0.1 pH unit. The narrow pH transition range advantageously provides a sharper pH response that can result in complete turn-on of the fluorophores with subtle changes of pH.
Accordingly, a single or series of pH-tunable, multicolored fluorescent nanoparticles having pH-induced micellization and quenching of fluorophores in the micelle core provide mechanisms for the independent control of pH transition (via polymers), fluorescence emission, or the use of fluorescence quenchers. The fluorescence wavelengths can be fine-tuned from, for example, violet to near IR emission range (400-820 nm). Their fluorescence ON/OFF activation can be achieved within no more than 0.25 pH units, which is much narrower compared to small molecular pH sensors. In some embodiments, a narrower range for fluorescence ON/OFF activation can be achieved such that the range is no more than 0.2 pH units. In some embodiments, the range is no more than 0.15 pH units. Furthermore, the use of a fluorescence quencher may also increase the fluorescence activation such that the difference between the associated and disassociated nanoparticle is greater than 50 times the associated nanoparticle. In some embodiments, the fluorescence activation is greater than 75 times higher than the associated nanoparticle This multicolored, pH tunable and activatable fluorescent nanoplatform provides a valuable tool to investigate fundamental cell physiological processes such as pH regulation in endocytic organelles, receptor cycling, and endocytic trafficking, which are related to cancer, lysosomal storage disease, and neurological disorders.
The size of the micelles will typically be in the nanometer scale (i.e., between about 1 nm and 1 μm in diameter). In some embodiments, the micelle has a size of about 10 to about 200 nm. In some embodiments, the micelle has a size of about 20 to about 100 nm. In some embodiments, the micelle has a size of about 30 to about 50 nm.
The micelles and nanoparticles may further comprise a targeting moiety. The targeting moiety may be used to target the nanoparticle or micelle to, for example, a particular cell surface receptor, cell surface marker, or to an organelle (e.g., nucleus, mitochondria, endoplasmic reticulum, chloroplast, apoplast, or peroxisome). Such targeting moieties will be advantageous in the study of receptor recycling, marker recycling, intracellular pH regulation, endocytic trafficking.
The targeting moiety may be, for example, an antibody or antibody fragment (e.g., Fab′ fragment), a protein, a peptide (e.g., a signal peptide), an aptamer, or a small molecule (e.g., folic acid). The targeting moiety may be conjugated to the block copolymer (e.g., conjugated to the hydrophilic polymer segment) by methods known in the art. The selection of targeting moiety will depend on the particular target. For example, antibodies, antibody fragments, small molecules, or binding partners may be more appropriate for targeting cell surface receptors and cell surface markers, whereas peptides, particularly signal peptides, may be more appropriate for targeting organelles.
Various aspects of the present disclosure relate to the direct or indirect detection of micelle disassociation by detecting an increase in a fluorescent signal. Techniques for detecting fluorescent signals from fluorescent dyes are known to those in the art. For example, fluorescence confocal microscopy as described in the Examples below is one such technique.
Flow cytometry, for example, is another technique that can be used for detecting fluorescent signals. Flow cytometry involves the separation of cells or other particles, such as microspheres, in a liquid sample. The basic steps of flow cytometry involve the direction of a fluid sample through an apparatus such that a liquid stream passes through a sensing region. The particles should pass one at a time by the sensor and may categorized based on size, refraction, light scattering, opacity, roughness, shape, fluorescence, etc.
The measurements described herein may include image processing for analyzing one or more images of cells to determine one or more characteristics of the cells such as numerical values representing the magnitude of fluorescence emission at multiple detection wavelengths and/or at multiple time points.
The present disclosure also provides kits. Any of the components disclosed herein may be combined in a kit. In certain embodiments the kits comprise a pH-responsive system or composition as described above.
The kits will generally include at least one vial, test tube, flask, bottle, syringe or other container, into which a component may be placed, and preferably, suitably aliquoted. Where there is more than one component in the kit, the kit also will generally contain a second, third or other additional containers into which the additional components may be separately placed. However, various combinations of components may be comprised in a container. In some embodiments, all of the micelle populations in a series are combined in a single container. In other embodiments, some or all of the micelle population in a series are provided in separate containers.
The kits of the present disclosure also will typically include packaging for containing the various containers in close confinement for commercial sale. Such packaging may include cardboard or injection or blow molded plastic packaging into which the desired containers are retained. A kit may also include instructions for employing the kit components. Instructions may include variations that can be implemented.
Radionuclide imaging modalities (positron emission tomography, (PET); single photon emission computed tomography (SPECT)) are diagnostic cross-sectional imaging techniques that map the location and concentration of radionuclide-labeled radiotracers. Although CT and MRI provide considerable anatomic information about the location and the extent of tumors, these imaging modalities cannot adequately differentiate invasive lesions from edema, radiation necrosis, grading or gliosis. PET and SPECT can be used to localize and characterize tumors by measuring metabolic activity.
PET and SPECT provide information pertaining to information at the cellular level, such as cellular viability. In PET, a patient ingests or is injected with a slightly radioactive substance that emits positrons, which can be monitored as the substance moves through the body. In one common application, for instance, patients are given glucose with positron emitters attached, and their brains are monitored as they perform various tasks. Since the brain uses glucose as it works, a PET image shows where brain activity is high.
Closely related to PET is single-photon emission computed tomography, or SPECT. The major difference between the two is that instead of a positron-emitting substance, SPECT uses a radioactive tracer that emits low-energy photons. SPECT is valuable for diagnosing coronary artery disease, and already some 2.5 million SPECT heart studies are done in the United States each year.
PET radiopharmaceuticals for imaging are commonly labeled with positron-emitters such as 11C, 13N, 15O, 18F, 82Rb, 62Cu, and 68Ga. SPECT radiopharmaceuticals are commonly labeled with positron emitters such as 99mTc, 201Tl, and 67Ga. Regarding brain imaging, PET and SPECT radiopharmaceuticals are classified according to blood-brain-barrier permeability (BBB), cerebral perfusion and metabolism receptor-binding, and antigen-antibody binding (Saha et al., 1994). The blood-brain-barrier SPECT agents, such as 99mTcO4-DTPA, 201Tl, and [67Ga]citrate are excluded by normal brain cells, but enter into tumor cells because of altered BBB. SPECT perfusion agents such as [123I]IMP, [99mTc]HMPAO, [99mTc]ECD are lipophilic agents, and therefore diffuse into the normal brain. Important receptor-binding SPECT radiopharmaceuticals include [123I]QNE, [123I]IBZM, and [123I]iomazenil. These tracers bind to specific receptors and are of importance in the evaluation of receptor-related diseases.
The following examples are included to demonstrate preferred embodiments of the disclosure. It should be appreciated by those of skill in the art that the techniques disclosed in the examples which follow represent techniques discovered by the inventor to function well in the practice of the disclosure, and thus can be considered to constitute preferred modes for its practice. However, those of skill in the art should, in light of the present disclosure, appreciate that many changes can be made in the specific embodiments which are disclosed and still obtain a like or similar result without departing from the spirit and scope of the disclosure.
1,4,7-Triazacyclononane-N,N′,N″-trisacetic acid (NOTA)- and ICG-conjugated poly(ethylene glycol)-b-poly(ethylpropylaminoethyl methacrylate) copolymer (aka UPS6.9 for pH transition at 6.9) was synthesized by the atom transfer radical polymerization method (
In aqueous saline solution (protein free), UPS6.9 copolymers undergo “reversible” micelle assembly/disassembly across a narrow pH span (<0.2 pH,
In biological milieu, serum protein binding can “irreversibly” arrest UPS copolymers in the dissociated unimer state upon pH activation of PEGylated micelles (
To investigate whether acidic pH can impact nanoprobe uptake inside cancer cells, 64Cu-UPS6.9 was incubated with HN5 head and neck cancer cells in DMEM medium at pH 6.5 and 7.4. To mimic the physiological environment, 40 mg/mL human serum albumin was added in the medium. For comparison, 64Cu-PEG-PLA nanoparticles were used as a non-pH sensitive control. HN5 cells were incubated with the same dose of either nanoparticles (25 μg/mL) for different time periods. Then the radioactive medium was replaced and washed with medium without the tracers. Autoradiography images of HN5 cells from the 96-well plate show pH-dependent uptake of 64Cu-UPS6.9. At pH 6.5, increased amount of positron signals was detected over time, leading to an approximately 5-fold increase in cell uptake at 1 h over that at pH 7.4 (
Spatio-temporal characterization of Cu-UPS6.9 distribution in orthotopic HN5 tumors in vivo further validated the capture and integration mechanism. HN5 cancer cells were inoculated in the submental space in the head and neck area of a SCID mouse. After tumors grew to 20-30 mm3, 64Cu-UPS6.9 tracer (0.1 mCi) was injected through the tail vein. At 30 mins, 3 h, and 24 h, animals were sacrificed, and tumors were removed and resected into 30 μm thin slices. Autoradiography analysis showed the initial sporadic capture of Cu-UPS6.9 in HN5 tumors (mostly at the tumor periphery) at 30 mins and 3 has verified by H&E histology, followed by increased tracer accumulation throughout the whole tumor at 24 h (
Brain cancer is one of the most lethal forms of cancer without a widely accepted method for early detection (Wen and Kesari, 2008). Late diagnosis when symptoms occur often leads to poor prognosis and survival (Omuro and DeAngelis, 2013). Conventional metabolic PET tracer FDG cannot be used for brain tumor imaging because of the high physiologic uptake of glucose in the normal brain tissues (Fink et al., 2015). To investigate the feasibility of 64Cu-UPS6.9 for glioma detection, evaluation of an orthotopic tumor xenograft model transplanted with green fluorescent protein (GFP)-transfected murine astrocyte with p53−/−, PTEN−/−, RB AFv600E mutations (73C) was undertaken. At 24 h after intravenous administration of 64Cu-UPS6.9, PET imaging showed a bright illumination of small sized brain tumors (˜10 mm3) over the dark normal brain tissue background (
To investigate the feasibility of 64Cu-UPS6.9 to image a broad set of cancers, PET imaging of additional head/neck and breast tumor nodules were evaluated. 64Cu-UPS6.9 tracers (0.1 mCi) were injected in the tail vein of tumor-bearing mice. Results show conspicuous detection of occult nodules (10-20 mm3) in orthotopic HN5 and FaDu head and neck tumors, as well as 4T1 triple negative breast tumors (
Biological processes are dynamic and complex with perpetual changes in space and time. The resulting spatio-temporal heterogeneity makes it challenging to accurately diagnose pathologic conditions. Previously an ICG-based ultra-pH sensitive (UPS) nanoprobe was reported for cancer detection by fluorescence imaging (Zhao et al., 2016). A binary fluorescent delineation of tumor margins was achieved, which led to accurate cancer surgery and prolonged survival in tumor-bearing mice. The main mechanism was thought to be the coupling of the pH dependent phase transition phenomenon to the quenching and unquenching of the fluorophores conjugated to the hydrophobic segment of the polymers. In this present disclosure, a 64Cu PET functional moiety was incorporated into the fluorescent nanoparticle formulation. In particular, the PET functional moiety was also conjugated to the hydrophobic segment of the polymers. Unlike the ON/OFF fluorescence reporter, the positron signals are always ‘ON’ and cannot be quenched, therefore phase transition-based changes in signal analogous to fluorescence were not expected. Contrary to expectation, the positron signal showed a binary pattern of background signal suppression and tumor activation similar to the fluorescence output (
Without wishing to be bound by theory, the improved sensitivity and specificity of cancer detection by 64Cu-UPS tracers is believed to be attributed to a “capture and integration” mechanism in the acidotic tumor milieu (
In summary, the molecular mechanism was determined for pH (proton) transistor-like nanoparticles to capture and integrate tumor acidotic signals into discrete outputs to improve the precision of cancer detection. This represents a second output, tissue retention, coupled to the transistor-like binary behavior of the UPS nanoparticles. The impact of the concept is illustrated by the non-invasive detection of small occult diseases (10-20 mm3 or 3-4 mm) in the brain, head and neck, and breast by PET imaging. Incorporation of both PET and fluorescence functions in one UPS nanoplatform further synergizes two orthogonal imaging modalities, which potentially allow initial whole-body assessment of tumor burden by PET, followed by high resolution fluorescence imaging for local interventions (e.g., biopsy or surgery). Besides diagnostic imaging, this second output for the UPS technology in binary dose retention may also offer therapeutic benefit in tumor-targeted delivery of radionuclides (e.g., 177Lu and 90Y) or drugs with increased area under the curve (AUC). It is anticipated that the proposed chemical integration algorithm will immediately impact early cancer detection and surveillance while creating strategic insights to incorporate molecular cooperativity principles (Li et al., 2018) for the design of precision medicine.
Poly(ethylene glycol)-b-poly(ethylpropylaminoethyl methacrylate) (PEG-b-PEPA) copolymer was synthesized following the reported procedure using the atom transfer radical polymerization method (Zhao et al., 2016). The polymers were then dissolved in methanol, ICG-Sulfo-OSu were first added to react with AMA (1:1 molar ratio) through via NHS-ester chemistry (Ma et al., 2014) for 1 hour. Next, p-SCN-Bn-NOTA were added to react with the remaining AMA (4:1 molar ratio) overnight at room temperature. Unconjugated ICG and NOTA were removed by Millipore ultrafiltration membranes with a molecular weight cutoff at 10 kDa. The UPS6.9 nanoprobes were produced by a solvent evaporation method (Wang et al., 2014) and concentrated to 5 mg/ml for further usage.
NOTA conjugated PEG-b-PLA block copolymer was synthesized by ring-opening polymerization following a published procedure (Blanco et al., 2010). Briefly, polymerization of D,L-lactide was performed at 110° C. using Fmoc-amine-PEG5K-hydroxyl as the macroinitiator and Sn(Oct)2 as a catalyst. Deprotection of Fmoc was made by 20% piperidine in DMF. After polymer purification with precipitating in ether for three times, the solid polymer was suspended in DMF and reacted with p-SCN-Bn-NOTA at room temperature overnight. Unconjugated NOTA was removed by Millipore ultrafiltration membranes with a molecular weight cutoff at 10 kDa.
Chelation of 64Cu2+ to NOTA on the UPS6.9 or PEG-b-PLA copolymer was accomplished by adjusting pH to 6.0-6.5 with 4 M ammonium acetate buffer for 15 mins at 37° C. Micelle formation was carried out by adjusting the solution pH to 7.4 with 2 M sodium carbonate. Removal of unbound 64CuCl2 was achieved by centrifugal membrane filtration with a molecular weight cutoff of 100 kD for three times. Before and after centrifugal filtration, 1 μL of micelle solution was mixed with 8 μL DI H2O and 1 μL of 50 mM diethylenetriamine pentaacetate (DTPA) for 5 minutes. A 2 μL aliquot of the mixture was then spotted on a TLC plate and eluted with the mobile phase (PBS). The labeling efficiency was determined by radio-TLC.
UPS6.9 polymers were first dissolved in 2.5 mL 0.1 M HCl and diluted to 2.0 mg/mL with DI water. Sodium chloride was added to adjust the salt concentration to 150 mM. pH titration was performed by adding small volumes (1 μL in increments) of 4.0 M NaOH solution with stirring. The pH increase through the range of 3-11 was monitored as a function of total added volume of NaOH. The fully protonated state and complete deprotonation states (protonation degree equaled 100 and 0%, respectively) were determined by the two extreme value points of pH titration curves' 1st derivation. The pH values were measured using a Mettler Toledo pH meter with a microelectrode. Next, UPS6.9 polymers with protonation degree at 50% were obtained by adding corresponding volumes of 4.0 M NaOH. 10 mL of polymer solution was centrifuged using ultra-centrifugation tube with a molecular weight cutoff at 100 kDa to ˜5 mL filtrated sample. pH titrations were performed to quantify the amount of polymer and degree of protonation in both residual and filtrate layers. The experiments were repeated three times and the data shown is in mean±s.d.
The cancer cell lines used for in vivo tumor models include HN5, FaDu, human head and neck cancers, 4T1 breast cancers, primary murine astrocyte cells with p53−/−, PTEN−/−, and BRAFV600E mutation (73C). HN5 and FaDu cell lines were obtained from Michael Story's lab; 4T1 were obtained from the David Boothman lab; 73C was obtained from the Woo-Ping Ge lab. All cells lines were tested for mycoplasma contamination before use. Negative status for contamination was verified by Mycoplasma Detection Kit from Biotool. Cells were cultured in DMEM or RPMI with 10% fetal bovine serum and antibiotics.
Animal protocols related to this study were reviewed and approved by the Institutional Animal Care and Use Committee. Female NOD-SCID mice (6-8 weeks) were purchased from UT Southwestern Medical Center Breeding Core. For orthotopic head and neck tumors, HN5 and FaDu (2×106 per mouse) were injected into the submental triangle area. One week after inoculation, animals with tumor size 20-100 mm3 were used for imaging studies. Orthotopic murine 4T1 breast tumor model was established in BalB/C mice by injection of 4T1 (5×105 per mouse) cells into the mammary fat pads. GFP-transfected 73C murine glioblastoma tumor model was established by implanting 73C glioma cells intracranially in the left hemisphere of mice. Gliomas (2-4 mm in diameter) were formed within two weeks in mice.
1.5×104HN5 cancer cells were seeded into individual well of 96-well plates (n=3 for each time point) containing 0.2 mL DMEM media for overnight before the nanoprobe incubation. 20 μg/mL Cu-UPS6.9 or Cu-PEG-PLA dispersed in either pH 6.5 or pH 7.4 DMEM medium containing 40 mg/mL human serum albumin were incubated with HN5 cells. At the specific time point, the cell wells were washed with cold PBS buffer three times to remove all the non-trapped nanoprobes. Finally, the 96-well plates were exposed on Perkin Elmer storage phosphor screens for overnight, then imaged using Typhoon imager for 64Cu tracer quantification. For confocal imaging, after nanoprobe incubation, the cells were fixed with 4% paraformaldehyde in PBS for 10 min at RT, and permeabilized with 0.1% Triton X-100 in PBS for 10 min at 4° C. Cells were then stained by Hoechst 33342, Anti-F-Actin, and Anti-LAMP1 for nucleus, cell membrane, and lysosomes, respectively. Anti-poly(ethylene glycol) antibody was used to label the UPS6.9 copolymer.
For 64Cu-UPS6.9, each mouse received ˜100 μCi of nanoprobes in 150 μL of saline intravenously via tail vein injection and PET/CT images were acquired 18-24 hours post-injection on the Siemens Inveon PET/CT Multi-Modality System for 15 mins. For FDG experiments, mice were fasted for 12 h prior to PET imaging. Each mouse received 150 μCi of FDG in 150 μL of saline intravenously via tail vein injection. PET/CT images were acquired one hour post-injection for 15 mins. The mice were sedated on the imaging bed under 2% isoflurane for the duration of imaging. Immediately after the CT data acquisition that was performed at 80 kV and 500 μA with a focal spot of 58 μm, 15-min static PET scans were conducted. The PET images were reconstructed using a Fourier Rebinning and Ordered Subsets Expectation Maximization 3D (OSEM3D) algorithm. Reconstructed CT and PET images were fused and analyzed using Inveon Research Workplace (IRW) software. PET images then were reconstructed into a single frame using the 3D Ordered Subsets Expectation Maximization (OSEM3D/MAP) algorithm. Regions of interest (ROI) were drawn manually as guided by CT encompassing the tumor in all planes containing the tissue. The target activity was quantitatively calculated as percentage injected dose per gram of tissue (% ID/g).
Immediately following PET imaging, the mice were sacrificed and tumor and major organs (e.g., the brain, liver, spleen, heart, kidney, muscle, etc.) were harvested and frozen. Section slides were prepared from each specimen. The slides were first exposed on Perkin Elmer storage phosphor screens, then imaged using Typhoon imager for 64Cu tracer quantification, followed by fluorescence imaging using a LICOR Odyssey flatbed scanner with an 800 nm filter for ICG signal, finally H&E staining was performed for histological correlation of the tumors.
Data are expressed as mean±s.d. Sample sizes were chosen to ensure adequate power (>85%, at significance of 0.05) to detect predicted effect sizes, which were estimated on the basis of either preliminary data or previous experiences with similar experiments. Differences between groups were assessed using paired, two-sided Student's t-tests for the calculation of P values.
Non-cancerous tissue inflammation (e.g., bacterial infection or tissue injury from surgery or radiation) frequently causes false positive PET results and contributes to patient worry and unnecessary testing with its attendant morbidity Inflammatory cells use glucose as a primary source of metabolic energy, and thus increased uptake of glucose and high rates of glycolysis are characteristic of inflamed tissue (Hess et al., 2014). In this study, a lipopolysaccharide (LPS)-induced, tumor-free animal model will be set up to investigate the imaging outcome of 64Cu-UPS at site of tissue inflammation. LPS-induced inflammation models have been widely used to study acute lung injury (de Prost et al., 2014 and Zhou et al., 2013), atherosclerosis (Rudd et al., 2010), and arthritis (Hsieh et al., 2011) by FDG-PET. In one study, LPS stimulation was shown to increase FDG uptake by 2.5-fold in macrophages (Tavakoli et al., 2013). In this study, LPS will be injected (50 μg in 20 μL of PBS; a low dose is used to avoid strong systemic inflammation) into the right hind leg muscles of C57BL/6 immunocompetent mice. At 2-4 h after injection, the serum will be collected and the pro-inflammatory cytokines will be analyzed (e.g., TNF-α and IL-10). The LPS dose will be reduced if the systemic cytokine level is high. On day 1 and 7, the animals will be imaged using FDG and Cu-UPS following the protocols as previously described for tumor imaging studies. For quantitative comparison of PET images, the left hind leg without LPS injection will be used as control. The values of % ID/g and SUV will be determined. After imaging, the leg muscles will be fixed in formalin and sectioned. The density of inflammatory cells (e.g., tissue-infiltrating macrophages) will be estimated in the tissue sections and correlate it with FDG and Cu-UPS signal intensity. It is anticipated that FDG will produce strong signals in inflamed tissues due to the high rate of glucose uptake in infiltrating inflammatory cells. In contrast, it is anticipated that the 64Cu-UPS signal will be low due to the fast clearance of protons by the healthy lymphatic system and limited nanoprobe extravasation at inflamed sites (unlike tumors with leakier vasculature and damaged lymphatics, aka extended permeation and retention effect; Fang et al., 2011 and Maeda et al., 2000).
It is possible that tissue inflammation can activate Cu-UPS through the high glycolysis rates of the inflammatory cells. If persistence of 64Cu-UPS signals in the LPS-injected site is observed, investigation of administration of taurine chloramine (TauCl) will be commenced, which has been shown to abrogate the FDG signals in macrophages after LPS stimulation (Kim et al., 2009). TauCl is generated and released from activated neutrophils following apoptosis, which exerts anti-inflammatory properties by inhibiting the production of inflammatory mediators (e.g., TNF-α; Kim et al., 2014 and Marcinkiewicz et al. 2014). TauCl will be tested to evaluate whether it can specifically decrease Cu-UPS signals in inflammatory cells.
In recent years, FDG-PET has been increasingly used to monitor therapeutic response in patients undergoing radiation or chemo-radiation therapy (Challapalli et al. 2016 and Weber, 2005). A notable clinical pain point for FDG-PET is the false positives arising from therapy (e.g., radiation-induced tissue inflammation), or false negatives from shrinking tumors after treatment. It is hypothesized that 64Cu-UPS-PET offers an accurate imaging method to monitor the antitumor efficacy of radiation and/or chemotherapy in selected head and neck cancer models. Feasibility of 64Cu-UPS-PET to predict the antitumor efficacy of small molecular inhibitors targeting acidosis pathways will be investigated. If successfully demonstrated, 64Cu-UPS-PET has the potential to predict tumor response to existing therapies including, but limited to, chemo-radiation therapy or novel small molecular tumor acidosis inhibitors, at an early stage in the course of therapy, thereby reducing the side effects and cost of ineffective therapy.
Various head and neck tumors may have different sensitivities toward chemo-radiation therapy. Depending on the 64Cu-UPS-PET response, the intensity of the therapy will be either increased or decreased and its effect on antitumor efficacy and treatment morbidity investigated. On the other hand, if chemo-radiation induces high levels of false positives/negatives in 64Cu-UPS-PET diagnosis, the mechanism will be identified, and mitigation strategy developed to minimize the false rates.
All of the compositions and methods disclosed and claimed herein can be made and executed without undue experimentation in light of the present disclosure. While the compositions and methods of this disclosure have been described in terms of certain embodiments, it will be apparent to those of skill in the art that variations may be applied to the compositions and methods and in the steps or in the sequence of steps of the methods described herein without departing from the concept, spirit and scope of the disclosure. More specifically, it will be apparent that certain agents which are both chemically and physiologically related may be substituted for the agents described herein while the same or similar results would be achieved. All such similar substitutes and modifications apparent to those skilled in the art are deemed to be within the spirit, scope and concept of the disclosure as defined by the appended claims.
The following references, to the extent that they provide exemplary procedural or other details supplementary to those set forth herein, are specifically incorporated herein by reference.
This application claims benefit of priority to U.S. Provisional Application Ser. No. 62/731,848, filed Sep. 15, 2018, the entire contents of which are hereby incorporated by reference.
This invention was made with government support under Grant Number RO1 CA192221 awarded by the National Institutes of Health. The government has certain rights in the invention.
| Number | Date | Country | |
|---|---|---|---|
| 62731848 | Sep 2018 | US |
