U.S. patent application number 16/653490 was filed with the patent office on 2020-09-17 for nanoparticle drug conjugates.
The applicant listed for this patent is Cornell University, Memorial Sloan Kettering Cancer Center. Invention is credited to Michelle S. Bradbury, Kai Ma, Ulrich Wiesner, Barney Yoo.
Application Number | 20200289668 16/653490 |
Document ID | / |
Family ID | 1000004860102 |
Filed Date | 2020-09-17 |
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United States Patent
Application |
20200289668 |
Kind Code |
A1 |
Bradbury; Michelle S. ; et
al. |
September 17, 2020 |
NANOPARTICLE DRUG CONJUGATES
Abstract
Described herein are nanoparticle drug conjugates (NDCs), which,
in certain embodiments, comprise a non-toxic, multi-modality,
clinically proven silica-based nanoparticle platform with
covalently attached drug molecules/moieties. The nanoparticle drug
conjugates (NDCs) demonstrate imaging capability and targeting
ligands which efficiently clear through the kidneys. Furthermore,
the conjugates incorporate therapeutic agents for cancer detection,
prevention, and/or treatment.
Inventors: |
Bradbury; Michelle S.; (New
York, NY) ; Yoo; Barney; (New York, NY) ;
Wiesner; Ulrich; (Ithaca, NY) ; Ma; Kai;
(Ithaca, NY) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Memorial Sloan Kettering Cancer Center
Cornell University |
New York
Ithaca |
NY
NY |
US
US |
|
|
Family ID: |
1000004860102 |
Appl. No.: |
16/653490 |
Filed: |
October 15, 2019 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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16137709 |
Sep 21, 2018 |
10485881 |
|
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16653490 |
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14722307 |
May 27, 2015 |
10111963 |
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16137709 |
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62094923 |
Dec 19, 2014 |
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62004738 |
May 29, 2014 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61K 31/506 20130101;
A61K 47/6923 20170801; A61K 49/0093 20130101; A61K 47/65 20170801;
A61K 47/60 20170801; A61K 31/5377 20130101; A61K 51/1244
20130101 |
International
Class: |
A61K 47/69 20060101
A61K047/69; A61K 31/506 20060101 A61K031/506; A61K 31/5377 20060101
A61K031/5377; A61K 47/65 20060101 A61K047/65; A61K 47/60 20060101
A61K047/60; A61K 49/00 20060101 A61K049/00; A61K 51/12 20060101
A61K051/12 |
Claims
1-19. (canceled)
20. A nanoparticle drug conjugate (NDC) comprising: a nanoparticle
having an average diameter from 5 nm to 10 nm that comprises a
silica-based core and a silica shell surrounding a least a portion
of the core; a linker moiety; a drug moiety; and one or more
targeting moieties, wherein the surface of the nanoparticle is
covalently modified with polyethylene glycol groups, and wherein
the drug moiety and linker moiety form a cleavable linker-drug
construct that is covalently linked to the nanoparticle.
21. The NDC of claim 20, wherein the linker moiety is enzyme
sensitive.
22. The NDC of claim 21, wherein the linker moiety is capable of
undergoing hydrolysis at the C-terminal end upon protease binding,
thereby releasing the drug moiety from the nanoparticle.
23. The NDC of claim 22, wherein the protease comprises a serine
protease or a cysteine protease.
24. The NDC of claim 22, wherein the average drug moiety to
nanoparticle ratio ranges from 1 to 20.
25. The NDC of claim 20, comprising from 1 to 20 targeting
moieties.
26. The NDC of claim 20, wherein the targeting moieties bind to
receptors on tumor cells.
27. The NDC of claim 20, further comprising a fluorescent
compound.
28. The NDC of claim 27, wherein the fluorescent compound is
Cy5.5.
29. The NDC of claim 20, wherein the nanoparticle is an
organo-silica core shell nanoparticle.
30. A method of treating of cancer comprising administering a
nanoparticle drug conjugate (NDC) comprising: a nanoparticle having
an average diameter from 5 nm to 10 nm that comprises a
silica-based core and a silica shell surrounding a least a portion
of the core; a linker moiety; a drug moiety; and one or more
targeting moieties, wherein the surface of the nanoparticle is
covalently modified with polyethylene glycol groups, and wherein
the drug moiety and linker moiety form a cleavable linker-drug
construct that is covalently linked to the nanoparticle.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation of U.S. patent
application Ser. No. 16/137,709 filed on Sep. 21, 2018, which is a
continuation of U.S. patent application Ser. No. 14/722,307 filed
on May 27, 2015, which claims priority to and the benefit of, and
incorporates herein by reference in their entireties, U.S.
Provisional Patent Application Nos. 62/004,738 and 62/094,923,
filed May 29, 2014 and Dec. 19, 2014, respectively.
FIELD OF THE INVENTION
[0002] This invention relates generally to nanoparticle conjugates
for delivery of therapeutic agents (e.g., targeted drug release)
for the detection, prevention, and treatment of cancer and other
diseases.
BACKGROUND OF THE INVENTION
[0003] Nanotherapeutic delivery vehicles are typically macro- or
supra-molecular multicomponent systems, ranging in size from
1-1,000 nm, that are either inherently therapeutic (e.g., no active
pharmaceutical ingredient) or function as therapeutic delivery
systems. To date, liposomal nanoparticles and biologics comprise a
large proportion of the number of FDA-approved products or products
in clinical trials used to treat a variety of cancer types, while a
number of polymer-based particle formulations are currently in
early phase trials.
[0004] Desirable candidates for nanotherapeutic delivery systems
share a common feature of incorporating and releasing a drug
compound in a controlled manner, which can favorably alter drug
bioavailability and pharmacokinetics, while minimizing off-target
toxicities. Ideally, an imaging label is incorporated therein to
assess their precise localization and retention at disease
sites.
[0005] However, these systems function using different mechanisms.
For example, antibody drug conjugates (ADCs) achieve lower drug
toxicity primarily through active targeting of tumor cells and
conditional release of drug molecules. Upon binding a cell surface
antigen, active drug release occurs after cellular internalization
and endosomal uptake. On the other hand, liposomes and
polymer-based drug delivery systems, which are typically much
larger assembled complexes (.about.20-150 nm diameters) passively
loaded with a greater payload (.about.10,000 drug molecules for
Doxil), have generally lacked targeting capabilities (BIND-014 is
an exception). Therefore, these complexes rely primarily on the
well-known enhanced permeability and retention (EPR) effect for the
successful delivery of nano-formulated drugs. While interstitial
permeation of liposomes may be poor due to their size, the free
drug is released through various mechanisms that are not entirely
understood. For example, Abraxane (.about.140 nm) relies on a
different approach to enhance the bioavailability of a hydrophobic
compound. In this case, a specific formulation of albumin and drug
(paclitaxel) forms the initial complex, which is in turn estimated
to disperse into smaller protein-drug aggregates upon
injection.
[0006] Thus, there is a need for a unique platform for drug
delivery that provides adequate biostability and exhibits
controlled release of the bioactive compound at a desired site.
SUMMARY OF THE INVENTION
[0007] Presented herein are methods and compositions of
nanoparticle drug conjugates (NDC), specifically silica-based
nanoparticle platform with covalently attached drug molecules. A
NDC has been demonstrated as a nanotherapeutic. The combination of
size, molecular composition and chemistry (e.g., mode of drug
release) may leverage the beneficial properties seen in other
nanotherapeutic products with the aim of overcoming key obstacles
hampering traditional formulations, including narrow therapeutic
indices, dose-limiting toxicities, and limited clinical
utility.
[0008] In one aspect, the invention is directed to a nanoparticle
drug conjugate (NDC) comprising: a nanoparticle (e.g., having a
diameter within a range from 1 nm to 25 nm); a linker moiety; and a
drug moiety (e.g., dasatinib or gefitinib, including any analog
thereof), wherein the nanoparticle is coated with an organic
polymer (e.g., wherein the organic polymer comprises at least one
bifunctionalized maleimide silyl-polyethylene glycol group attached
to at least one linker-drug construct), and wherein the drug moiety
and linker moiety form a cleavable (e.g., via a protease)
linker-drug construct that is covalently linked to the nanoparticle
(e.g., via the linker moiety) (e.g., wherein the average drug
moiety to nanoparticle ratio ranges from 1 to 20).
[0009] In certain embodiments, the linker moiety comprises one or
more amino acids (e.g., a peptide or polypeptide) (e.g., from 1 to
10 amino acids). In certain embodiments, the linker moiety
comprises (Amino-(spacer).sub.x).sub.y-peptide or
(spacer).sub.z-peptide [e.g., dipeptide (e.g.,
phenylalanine-arginine (Phe-Arg) or phenylalanine-lysine
(Phe-Lys))] wherein the spacer has from 2 to 50 atoms (e.g.,
wherein the spacer is PEG), wherein x is an integer from 1 to 5,
wherein y is an integer from 1 to 5, wherein z is an integer from 5
to 15, and wherein the linker moiety comprises a degradable moiety
(e.g., an amide bond) between the linker moiety and the drug moiety
(e.g., allowing cleavage of the drug moiety in the presence of a
protease). In certain embodiments, the linker moiety comprises a
spacer (e.g., polyethylene glycol (PEG)), PEG.sub.2,
para-aminobenzyloxy carbamate (PABC)) between a peptide and the
drug moiety. In certain embodiments, the NDCs further comprise a
fluorescent compound (e.g., associated with the nanoparticle, e.g.,
within the core of the nanoparticle). In certain embodiments, the
NDCs further comprise a radiolabel.
[0010] In certain embodiments, the linker moiety is capable of
undergoing hydrolysis at the C-terminal end upon protease (e.g.,
serine protease (e.g., trypsin), cysteine protease (e.g., cathepsin
B)) binding, thereby releasing the drug moiety from the
nanoparticle.
[0011] In certain embodiments, the drug moiety comprises a receptor
tyrosine kinase (RTK) inhibitor (e.g., dasatinib or gefitinib,
including any analog thereof (e.g., any pharmaceutical and/or
therapeutic equivalent thereof) modified to provide attachment to
the linker moiety without perturbing underlying chemical structure
of an active binding site of the drug moiety).
[0012] In certain embodiments, the NDCs further comprise from 1 to
20 targeting moieties (e.g., cyclic arginylglycylaspartic acid
(cRGD)), wherein the targeting moieties bind to receptors on tumor
cells.
[0013] In certain embodiments, the NDC is a theranostic.
[0014] In certain embodiments, the fluorescent compound is
Cy5.5.
[0015] In certain embodiments, the drug moiety is attached to the
radiolabel.
[0016] In certain embodiments, the nanoparticle further comprises a
silica-based core and a silica shell surrounding a least a portion
of the core.
[0017] Elements of embodiments described with respect to a given
aspect of the invention may be used in various embodiments of
another aspect of the invention. For example, it is contemplated
that features of dependent claims depending from one independent
claim can be used in apparatus and/or methods of any of the other
independent claims.
BRIEF DESCRIPTION OF THE DRAWINGS
[0018] FIG. 1A depicts chemical structures of gefitinib and
analogues (APdMG 1 and dPEG.sub.2APdMG 2).
[0019] FIG. 1B depicts a chemical structure of linker-drug directly
connected through amide bond (Phe-Arg-APdMG 3).
[0020] FIG. 1C depicts a chemical structure of linker-drug
connected through dPEG.sub.2 spacer (Phe-Arg-dPEG.sub.2APdMG
4).
[0021] FIG. 1D depicts a chemical structure of linker-drug
connected through degradable PABC spacer (Phe-Lys-PABC-APdMG 5)
[0022] FIGS. 2A-2C show linker types.
[0023] FIG. 2A depicts that Phe-Arg-APdMG utilizes an amide bond
for drug attachment. Enzymes recognize and bind the dipeptide
sequence (Phe-Arg) then hydrolyze the amide bond C-terminal to the
dipeptide and release APdMG 1.
[0024] FIG. 2B shows that Phe-Arg-dPEG.sub.2APdMG uses
dPEG.sub.2APdMG 2, which incorporates a longer 10 atom PEG spacer
between the drug and dipeptide to enhance drug release.
[0025] FIG. 2C shows that Phe-Lys-PABC-APdMG utilizes a
para-aminobenzoxy-carbamate (or PABC) spacer group between the
dipeptide (Phe-Lys) and aminopropyl-dMG. After enzyme catalyzed
release of the spacer-drug, the spacer spontaneously decomposes
from the drug.
[0026] FIGS. 3A-3C are representative enzyme (trypsin) catalyzed
release of drug from linker-drug constructs. Data indicates that
APdMG and dPEG.sub.2APdMG are released from the constructs.
Retention times are indicated in parenthesis. Trypsin assays were
conducted at 37.degree. C. in 10 mM phosphate buffer (pH 7.2)
[0027] FIG. 3A shows LCMS data of Phe-Arg-APdMG 3 (top) and
Phe-Arg-APdMG+trypsin for 60 mins (bottom).
[0028] FIG. 3B shows LCMS data of Phe-Arg-dPEG.sub.2-APdMG 4 (top)
and Phe-Arg-dPEG.sub.2-APdMG+trypsin for 10 mins (bottom).
[0029] FIG. 3C shows LCMS data of Phe-Arg-PABC-APdMG 5 (top) and
Phe-Arg-PABC-APdMG+trypsin for 10 mins (bottom).
[0030] FIGS. 4A and 4B show in vitro drug release assays for free
linker-drug constructs Phe-Arg-APdMG, Phe-Arg-dPEG.sub.2APdMG, and
Phe-Lys-PABC-APdMG, monitored over time by HPLC at 348 nm. % Free
Drug is the drug released divided by the initial drug load of the
linker-drug construct determined at 348 nm.
[0031] FIG. 4A depicts free linker-drug constructs treated with
trypsin. Trypsin assays were conducted in 10 mM phosphate buffer
(pH 7.2) at 37.degree. C.
[0032] FIG. 4B depicts free linker-drug construct treated with
cathepsin B. Cathepsin B assays were conducted in 25 mM sodium
acetate buffer (pH 5.0).
[0033] FIGS. 5A and 5B show representative HPLC profiles of in
vitro drug release from NDCs in the presence of trypsin. NDCs were
treated with trypsin then analyzed by HPLC after 5 and 120 min.
Data indicates that compounds 2 or 3 are released from the C'dots.
Trypsin assays were conducted in 10 mM phosphate buffer (pH 7.2) at
37.degree. C. HPLC analysis at 348 nm.
[0034] FIG. 5A shows HPLC profile of NDC 6
[0035] FIG. 5B shows HPLC profile of NDC 7.
[0036] FIGS. 6A and 6B depict in vitro drug release from NDCs in
the presence of enzymes. Enzymatic reactions were monitored over
time by HPLC at 348 nm. Trypsin assays were conducted in 10 mM
phosphate buffer (pH 7.2) at 37.degree. C.; cathepsin B assays were
conducted in 25 mM sodium acetate buffer (pH 5.0) at 37.degree.
C.
[0037] FIG. 6A shows drug release of
C'dot-(Cy5)-PEG-Phe-Arg-dPEG.sub.2APdMG 6 treated with trypsin.
[0038] FIG. 6B shows drug release of
C'dot-(Cy5)-PEG-Phe-Lys-PABC-APdM 7 treated with cathepsin B.
[0039] FIG. 7 shows western blot analysis of H1650 cells treated
with gefitinib, C'dot-(Cy5)-PEG-Phe-Arg-dPEG.sub.2APdMG 6, and
C'dot-(Cy5)-PEG-Phe-Lys-PABC-APdMG 7. Cells treated with gefitinib
or specified NDC at indicated concentrations for 18 hrs followed by
EGF (50 ng/mL) for 5 minutes (pEGFR--phosphorylated EGFR;
tEGFR--total EGFR).
[0040] FIG. 8 shows radioGPC of
C'dot-(Cy5)-PEG-Phe-Arg-dPEG.sub.2-Gly-D-Tyr(.sup.131I)-APdMG 8.
Radiochemical yield of >90% based on peak integrations. The
smaller peak is presumed to be residual free .sup.131I.
[0041] FIGS. 9A and 9B show linker-drug constructs,
Phe-Arg-dPEG.sub.2-D-Tyr-aminopropyl-dMG and
Phe-Lys-PABC-D-Tyr-aminopropyl-dMG that incorporate a D-tyrosine
residue with the drug component for attaching a radiolabel
(compounds 23 and 24).
[0042] FIG. 10 shows Scheme 1, which illustrates enzyme-mediated
drug release from nanoparticle drug conjugate (NDC).
[0043] FIG. 11 shows Scheme 2, which illustrates that
C'dots-(Cy5)-PEG-mal are reacted with linker-drug constructs
Phe-Arg-dPEG2APdMG 4 and Phe-Lys-PABC-APdMG 5 resulting in the NDCs
C'dot-(Cy5)-PEG-Phe-Arg-dPEG.sub.2APdMG 6 and
C'dot-(Cy5)-PEG-Phe-Lys-PABC-APdMG 7.
[0044] FIG. 12 shows Scheme 3, which illustrates a synthesis
process of APdMG 1.
[0045] FIG. 13 shows Scheme 4, which illustrates a synthesis
process of dPEG.sub.2APdMG 2.
[0046] FIG. 14 shows Scheme 5, which illustrates a synthesis
process of Phe-Arg-APdMG 3 and Phe-Arg-dPEG.sub.2APdMG 4.
[0047] FIG. 15 shows Scheme 6, which illustrates a synthesis
process of Phe-Lys-PABC-APdMG (5).
[0048] FIGS. 16A-16D shows characterization of mal-PEG-C' dots and
NDC 6 and 7.
[0049] FIG. 16A shows analytical C18 reversed phase HPLC at 348
nm.
[0050] FIG. 16B shows a TEM image.
[0051] FIG. 16C shows absorbance and emission spectra.
[0052] FIG. 16D shows FCS correlation curves.
[0053] The features and advantages of the present disclosure will
become more apparent from the detailed description set forth below
when taken in conjunction with the drawings, in which like
reference characters identify corresponding elements throughout. In
the drawings, like reference numbers generally indicate identical,
functionally similar, and/or structurally similar elements.
Definitions
[0054] In order for the present disclosure to be more readily
understood, certain terms are first defined below. Additional
definitions for the following terms and other terms are set forth
throughout the specification.
[0055] In this application, the use of "or" means "and/or" unless
stated otherwise. As used in this application, the term "comprise"
and variations of the term, such as "comprising" and "comprises,"
are not intended to exclude other additives, components, integers
or steps. As used in this application, the terms "about" and
"approximately" are used as equivalents. Any numerals used in this
application with or without about/approximately are meant to cover
any normal fluctuations appreciated by one of ordinary skill in the
relevant art.
[0056] In certain embodiments, the term "approximately" or "about"
refers to a range of values that fall within 25%, 20%, 19%, 18%,
17%, 16%, 15%, 14%, 13%, 12%, 11%, 10%, 9%, 8%, 7%, 6%, 5%, 4%, 3%,
2%, 1%, or less in either direction (greater than or less than) of
the stated reference value unless otherwise stated or otherwise
evident from the context (except where such number would exceed
100% of a possible value).
[0057] The term "administration" refers to introducing a substance
into a subject. In general, any route of administration may be
utilized including, for example, parenteral (e.g., intravenous),
oral, topical, subcutaneous, peritoneal, intraarterial, inhalation,
vaginal, rectal, nasal, introduction into the cerebrospinal fluid,
or instillation into body compartments. In some embodiments,
administration is oral. Additionally or alternatively, in some
embodiments, administration is parenteral. In some embodiments,
administration is intravenous.
[0058] The term "agent" refers to a compound or entity of any
chemical class including, for example, polypeptides, nucleic acids,
saccharides, lipids, small molecules, metals, or combinations
thereof. As will be clear from context, in some embodiments, an
agent can be or comprise a cell or organism, or a fraction,
extract, or component thereof. In some embodiments, an agent is or
comprises a natural product in that it is found in and/or is
obtained from nature. In some embodiments, an agent is or comprises
one or more entities that are man-made in that it is designed,
engineered, and/or produced through action of the hand of man
and/or are not found in nature. In some embodiments, an agent may
be utilized in isolated or pure form; in some embodiments, an agent
may be utilized in crude form. In some embodiments, potential
agents are provided as collections or libraries, for example that
may be screened to identify or characterize active agents within
them. Some particular embodiments of agents that may be utilized
include small molecules, antibodies, antibody fragments, aptamers,
siRNAs, shRNAs, DNA/RNA hybrids, antisense oligonucleotides,
ribozymes, peptides, peptide mimetics, peptide nucleic acids, small
molecules, etc. In some embodiments, an agent is or comprises a
polymer. In some embodiments, an agent contains at least one
polymeric moiety. In some embodiments, an agent comprises a
therapeutic, diagnostic and/or drug.
[0059] The term "peptide" or "polypeptide" refers to a string of at
least two (e.g., at least three) amino acids linked together by
peptide bonds. In some embodiments, a polypeptide comprises
naturally-occurring amino acids; alternatively or additionally, in
some embodiments, a polypeptide comprises one or more non-natural
amino acids (i.e., compounds that do not occur in nature but that
can be incorporated into a polypeptide chain; see, for example,
http://www.cco.caltech.edu/dadgrp/Unnatstruct.gif, which displays
structures of non-natural amino acids that have been successfully
incorporated into functional ion channels) and/or amino acid
analogs as are known in the art may alternatively be employed). In
some embodiments, one or more of the amino acids in a protein may
be modified, for example, by the addition of a chemical entity such
as a carbohydrate group, a phosphate group, a farnesyl group, an
isofarnesyl group, a fatty acid group, a linker for conjugation,
functionalization, or other modification, etc.
[0060] As used herein, the term "associated" typically refers to
two or more entities in physical proximity with one another, either
directly or indirectly (e.g., via one or more additional entities
that serve as a linking agent), to form a structure that is
sufficiently stable so that the entities remain in physical
proximity under relevant conditions, e.g., physiological
conditions. In some embodiments, associated moieties are covalently
linked to one another. In some embodiments, associated entities are
non-covalently linked. In some embodiments, associated entities are
linked to one another by specific non-covalent interactions (i.e.,
by interactions between interacting ligands that discriminate
between their interaction partner and other entities present in the
context of use, such as, for example. streptavidin/avidin
interactions, antibody/antigen interactions, etc.). Alternatively
or additionally, a sufficient number of weaker non-covalent
interactions can provide sufficient stability for moieties to
remain associated. Exemplary non-covalent interactions include, but
are not limited to, electrostatic interactions, hydrogen bonding,
affinity, metal coordination, physical adsorption, host-guest
interactions, hydrophobic interactions, pi stacking interactions,
van der Waals interactions, magnetic interactions, electrostatic
interactions, dipole-dipole interactions, etc.
[0061] As used herein, "biodegradable" materials are those that,
when introduced into cells, are broken down by cellular machinery
(e.g., enzymatic degradation) or by hydrolysis into components that
cells can either reuse or dispose of without significant toxic
effects on the cells. In certain embodiments, components generated
by breakdown of a biodegradable material do not induce inflammation
and/or other adverse effects in vivo. In some embodiments,
biodegradable materials are enzymatically broken down.
Alternatively or additionally, in some embodiments, biodegradable
materials are broken down by hydrolysis. In some embodiments,
biodegradable polymeric materials break down into their component
polymers. In some embodiments, breakdown of biodegradable materials
(including, for example, biodegradable polymeric materials)
includes hydrolysis of ester bonds. In some embodiments, breakdown
of materials (including, for example, biodegradable polymeric
materials) includes cleavage of urethane linkages.
[0062] As used herein, a "functional" biological molecule is a
biological molecule in a form in which it exhibits a property
and/or activity by which it is characterized. A biological molecule
may have two functions (i.e., bifunctional) or many functions
(i.e., multifunctional).
[0063] The term "in vitro" as used herein refers to events that
occur in an artificial environment, e.g., in a test tube or
reaction vessel, in cell culture, etc., rather than within a
multi-cellular organism.
[0064] As used herein "in vivo" refers to events that occur within
a multi-cellular organism, such as a human and a non-human animal.
In the context of cell-based systems, the term may be used to refer
to events that occur within a living cell (as opposed to, for
example, in vitro systems).
[0065] The term "imaging agent" as used herein refers to any
element, molecule, functional group, compound, fragments thereof or
moiety that facilitates detection of an agent (e.g., a
polysaccharide nanoparticle) to which it is joined. Examples of
imaging agents include, but are not limited to: various ligands,
radionuclides (e.g., .sup.3H, .sup.14C, .sup.18F, .sup.19F,
.sup.32P, .sup.35S, .sup.135I, .sup.125I, .sup.123I, .sup.64Cu,
.sup.187Re, .sup.111In, .sup.90Y, .sup.99mTc, .sup.177Lu, .sup.89Zr
etc.), fluorescent dyes (for specific exemplary fluorescent dyes,
see below), chemiluminescent agents (such as, for example,
acridinum esters, stabilized dioxetanes, and the like),
bioluminescent agents, spectrally resolvable inorganic fluorescent
semiconductors nanocrystals (i.e., quantum dots), metal
nanoparticles (e.g., gold, silver, copper, platinum, etc.)
nanoclusters, paramagnetic metal ions, enzymes (for specific
examples of enzymes, see below), colorimetric labels (such as, for
example, dyes, colloidal gold, and the like), biotin, dioxigenin,
haptens, and proteins for which antisera or monoclonal antibodies
are available. Non-limiting fluorescent compounds that may be used
in the present invention include, Cy5, Cy5.5 (also known as Cy5++),
Cy2, fluorescein isothiocyanate (FITC), tetramethylrhodamine
isothiocyanate (TRITC), phycoerythrin, Cy7, fluorescein (FAM), Cy3,
Cy3.5 (also known as Cy3++), Texas Red, LightCycler-Red 640,
LightCycler Red 705, tetramethylrhodamine (TMR), rhodamine,
rhodamine derivative (ROX), hexachlorofluorescein (HEX), rhodamine
6G (R6G), the rhodamine derivative JA133, Alexa Fluorescent Dyes
(such as Alexa Fluor 488, Alexa Fluor 546, Alexa Fluor 633, Alexa
Fluor 555, and Alexa Fluor 647), 4',6-diamidino-2-phenylindole
(DAPI), Propidium iodide, AMCA, Spectrum Green, Spectrum Orange,
Spectrum Aqua, Lissamine, and fluorescent transition metal
complexes, such as europium.
[0066] As used herein, the term "nanoparticle" refers to a particle
having a diameter of less than 1000 nanometers (nm). In some
embodiments, a nanoparticle has a diameter of less than 300 nm, as
defined by the National Science Foundation. In some embodiments, a
nanoparticle has a diameter of less than 100 nm as defined by the
National Institutes of Health. In some embodiments, nanoparticles
are micelles in that they comprise an enclosed compartment,
separated from the bulk solution by a micellar membrane, typically
comprised of amphiphilic entities which surround and enclose a
space or compartment (e.g., to define a lumen). In some
embodiments, a micellar membrane is comprised of at least one
polymer, such as for example a biocompatible and/or biodegradable
polymer.
[0067] As used herein, the term "subject" includes humans and
mammals (e.g., mice, rats, pigs, cats, dogs, and horses). In many
embodiments, subjects are mammals, particularly primates,
especially humans. In some embodiments, subjects are livestock such
as cattle, sheep, goats, cows, swine, and the like; poultry such as
chickens, ducks, geese, turkeys, and the like; and domesticated
animals particularly pets such as dogs and cats. In some
embodiments (e.g., particularly in research contexts) subject
mammals will be, for example, rodents (e.g., mice, rats, hamsters),
rabbits, primates, or swine such as inbred pigs and the like.
[0068] As used herein, the term "treatment" (also "treat" or
"treating") refers to any administration of a substance that
partially or completely alleviates, ameliorates, relives, inhibits,
delays onset of, reduces severity of, and/or reduces incidence of
one or more symptoms, features, and/or causes of a particular
disease, disorder, and/or condition. Such treatment may be of a
subject who does not exhibit signs of the relevant disease,
disorder and/or condition and/or of a subject who exhibits only
early signs of the disease, disorder, and/or condition.
Alternatively or additionally, such treatment may be of a subject
who exhibits one or more established signs of the relevant disease,
disorder and/or condition. In some embodiments, treatment may be of
a subject who has been diagnosed as suffering from the relevant
disease, disorder, and/or condition. In some embodiments, treatment
may be of a subject known to have one or more susceptibility
factors that are statistically correlated with increased risk of
development of the relevant disease, disorder, and/or
condition.
DETAILED DESCRIPTION
[0069] Described herein are nanoparticle drug conjugates (NDCs),
which, in certain embodiments, comprise a non-toxic,
multi-modality, clinically proven silica-based nanoparticle
platform with covalently attached drug molecules/moieties. The
nanoparticle drug conjugates (NDCs) demonstrate imaging
capabilities and targeting ligands which efficiently clear through
the kidneys. Furthermore, the conjugates incorporate therapeutic
agents for cancer detection, prevention, and/or treatment. For
example, NDCs containing specific receptor tyrosine kinase (RTK)
inhibitors have been synthesized and are demonstrated to release
drug compounds in a controlled and predictable manner. Furthermore,
western blot analysis shows reduced RTK phosphorylation levels in
cells, suggesting NDC based drug delivery in vitro.
[0070] In some embodiments, the silica-based nanoparticle platform
comprises ultrasmall nanoparticles or "C dots," which are
fluorescent, organo-silica core shell particles that have diameters
controllable down to the sub-10 nm range with a range of modular
functionalities. C dots are described by U.S. Pat. No. 8,298,677 B2
"Fluorescent silica-based nanoparticles", U.S. Publication No.
2013/0039848 A1 "Fluorescent silica-based nanoparticles", and U.S.
Publication No. US 2014/0248210 A1 "Multimodal silica-based
nanoparticles", the contents of which are incorporated herein by
reference in their entireties. Incorporated into the silica matrix
of the core are near-infrared dye molecules, such as Cy5.5, which
provides its distinct optical properties. Surrounding the core is a
layer or shell of silica. The silica surface is covalently modified
with silyl-polyethylene glycol (PEG) groups to enhance stability in
aqueous and biologically relevant conditions. These particles have
been evaluated in vivo and exhibit excellent clearance properties
owing largely to their size and inert surface. Among the additional
functionalities incorporated into C dots are chemical sensing,
non-optical (PET) image contrast and in vitro/in vivo targeting
capabilities, which enable their use in visualizing lymph nodes for
surgical applications, and melanoma detection in cancer.
[0071] C dots provide a unique platform for drug delivery due to
their physical properties as well as demonstrated human in vivo
characteristics. These particles are ultrasmall and benefit from
EPR effects in tumor microenvironments, while retaining desired
clearance and pharmacokinetic properties. To this end, described
herein is a nanoparticle drug delivery system in which, in certain
embodiments, drug constructs are covalently attached to C dots (or
other nanoparticles). C dot-based NDCs for drug delivery provide
good biostability, minimize premature drug release, and exhibit
controlled release of the bioactive compound. In certain
embodiments, peptide-based linkers are used for NDC applications.
These linkers, in the context of antibodies and polymers, are
stable both in vitro and in vivo, with highly predictable release
kinetics that rely on enzyme catalyzed hydrolysis by lysosomal
proteases. For example, cathepsin B, a highly expressed protease in
lysosomes, can be utilized to facilitate drug release from
macromolecules. By incorporating a short, protease sensitive
peptide between the macromolecular backbone and the drug molecule,
controlled release of the drug can be obtained in the presence of
the enzyme.
[0072] In certain embodiments, the NDCs are ultrasmall (e.g., with
average diameter from about 5 nm to about 10 nm, (e.g., about 6
nm)) and utilize enzyme sensitive linkers, for example, where drug
release is catalyzed by proteases. In one example, gefitinib, an
important epidermal growth factor receptor mutant
(EGFRmt+)-tyrosine kinase inhibitor (TKI) cancer drug, was modified
and incorporated onto the particles. The resulting NDCs exhibited
excellent in vitro stability, solubility, and proved to be active
in EGFRmt+-expressing NSCLC cells.
[0073] In certain embodiments, the NDCs comprise one or more
targeting moieties, for example, to target a particular tissue type
(e.g., a particular tumor). NDCs with target moieties enhance
internalization of drugs in tumor cells (e.g., targeting ligands
bind to receptors on tumor cells, and/or deliver drugs into tumor
cells (e.g., by increased permeability)). For example, to create a
particle therapeutic with an additional targeting moiety (e.g.,
cRGD), silica nanoparticles are added to a mixture of cRGDY-PEG
conjugates and maleimide bifunctionalized PEGs. The maleimide
bifunctionalized PEGs support the additional attachment of
drug-linker conjugates to create a theranostic product.
[0074] In some embodiments, ultrasmall particles may be associated
with PET labels and/or optical probes. Nanoparticles may be
observed in vivo (e.g., via PET) to evaluate drug accumulation in a
target site. For example, nanoparticles with PET labels (e.g.,
without drug substances) may be administered first. Then, by
analyzing the in vivo PET images of the nanoparticles, drug (e.g.,
conjugated with nanoparticles) concentration and accumulation rate
in the tumor may be estimated. The dose may be determined based on
the obtained estimation to provide personalized medicine (e.g.,
tumor size rather than the patient's body weight). In some
embodiments, a radiolabeled drug may be traced in vivo. A highly
concentrated chemotherapy drug is potentially dangerous if it is
not targeted. In some embodiments, nanoparticles with optical
probes (e.g., fluorophore) may be used for intraoperative imaging
(e.g., where surface of tissue/tumor is exposed) and/or biopsies of
tumors.
[0075] The therapeutic agent and nanoparticle can be radiolabeled
or optically labelled separately, allowing independent monitoring
of the therapeutic agent and the nanoparticle. In one embodiment,
radiofluorinated (i.e., .sup.18F) dasatinib is coupled with
PEG-3400 moieties attached to the nanoparticle via NHS ester
linkages. Radiofluorine is crucial for being able to independently
monitor time-dependent changes in the distribution and release of
the drug from the radioiodinated C24I) fluorescent (Cy5)
nanoparticle. In this way, the pro drug (dasatinib) and
nanoparticle can be monitored. This permits optimization of the
prodrug design compared with methods in the prior art where no
dual-labeling approach is used. In another embodiment,
radiotherapeutic iodine molecules (e.g., .sup.131I), or other
therapeutic gamma or alpha emitters, are conjugated with PEG via a
maleimide functional group, where the therapeutic agent may not
dissociate from the PEG in vivo.
[0076] NDCs are drug compounds covalently attached to C dot
nanoparticles (or other nanoparticles) through a molecular linker.
In certain embodiments, linkers incorporate peptide (e.g.,
dipeptide) sequences sensitive to trypsin (control enzyme) and/or
cathepsin B, which is an enzyme found predominantly in the
lysosomes of cells. Experiments involving two classes of linker
chemistries are described herein for controlled drug release--one
incorporating an amide bond between the linker and drug; and
another utilizing a degradable moiety between the linker and drug.
In some embodiments, the linkers are designed to release the drug
from the nanoparticle (e.g., C dot) under particular conditions,
for example, proteolytic hydrolysis.
[0077] Example drugs that can be used include RTK inhibitors, such
as dasatinib and gefitinib, can target either platelet-derived
growth factor receptor (PDGFR) or EGFRmt+ expressed by primary
tumor cells of human or murine origin (e.g., genetically engineered
mouse models of high-grade glioma, neurospheres from human patient
brain tumor explants) and/or tumor cell lines of non-neural origin.
Dasatinib and gefitinib analogs can be synthesized to enable
covalent attachment to several linkers without perturbing the
underlying chemical structure defining the active binding site.
[0078] Synthetic approaches were validated and the desired
linker-drug constructs and NDCs were obtained. HPLC/LCMS methods
for NDC characterization and enzyme release assays were also
developed. In vitro enzyme drug release assays revealed a number of
important structural factors in NDC design. For example, spacing
between C dot and linker was varied using different sized PEG
chains, and revealed that sufficient spacing between C dot and
linker was important to allow for enzyme catalyzed drug release.
Similarly, the spacing between linker and drug was also found to be
important for enzyme mediated release. Moreover, linker designs
utilizing a degradable moiety between the linker and drug exhibited
significantly faster release kinetics than those where a simple
amide bond was used. In some embodiments, the degradable moiety can
be a carbohydrates and/or any linker that can be enzymatically
cleaved and/or activated.
[0079] Cell-based assays were also performed. Linker-drug
constructs and NDCs incorporating either dasatinib or gefitinib
analogs were tested against primary brain tumor cells
(neurospheres) and/or tumor cell lines metastasizing to the brain
(e.g., lung, squamous cell cancers). Phosphorylation levels of
EGFRmt+ were reduced or ablated in cell lines exposed to NDCs as
well as the free linker-drug constructs, and NDCs exhibited more
potent inhibitory activity than the native drug in some cases.
[0080] In one aspect, a nanoparticle drug conjugate (NDC)
comprising a drug moiety, a linker moiety, and a nanoparticle,
wherein the drug moiety is covalently linked to the nanoparticle
via the linker moiety is described herein. In certain embodiments,
the NDC comprises an amide bond and/or degradable moiety between
the linker moiety and the drug moiety. In certain embodiments, the
linker moiety comprises a peptide (e.g., a dipeptide). In certain
embodiments, the linker moiety provides hydrolysis at the
C-terminal end upon protease binding, thereby releasing the drug
moiety from the nanoparticle. In certain embodiments, the drug
moiety comprises a receptor tyrosine kinase (RTK) inhibitor (e.g.,
dasatinib or gefitinib, including any analog thereof, e.g., any
pharmaceutical and/or therapeutic equivalent thereof, modified to
provide attachment to the linker moiety without perturbing
underlying chemical structure of an active binding site of the drug
moiety). In certain embodiments, the nanoparticle is a newer
generation C dot or a C' dot. In another aspect, the invention is
directed to a method of detection, prevention, and/or treatment of
a disease (e.g., cancer) comprising administration and/or detection
of the NDC of any of the embodiments described herein.
[0081] Nano-sized drug delivery vehicles are appealing due to (1)
their small sizes, enabling trafficking throughout the body as well
as within the cells; (2) their high surface area to volume ratios,
enabling cargo loading and release; and (3) their tunable surface
chemistries, enhancing solubility, controlling binding, and
incorporating biologically active functionalities.
[0082] In vivo nanoparticle drug delivery is fraught with a host of
biophysical and biochemical challenges that can cause particle
uptake (opsonization), excretion (kidneys) or non-specific loss
(extravasation), and prevent the therapeutic payload from reaching
the desired cells. One of the key parameters of a drug delivery
construct is its physical size, where smaller particles (e.g.,
particles less than or equal to about 5 nm hydrodynamic diameter)
can extravasate non-specifically, while much larger particles or
aggregates (e.g., particles or aggregates greater than or equal to
about 500 nm diameter) can become lodged in the microvasculature,
rather than being trafficked to their intended targets. For
non-biodegradable materials, it is found that there is a preferable
diameter range from 5 nm to 10 nm enabling renal filtration as a
means of particle removal, while limiting the rate of renal
clearance to enable the desired pharmacokinetics. Additionally, it
was found that particles of this size regime can also take
advantage of an enhanced permeability and retention (EPR) effect,
that is, the passive accumulation of macromolecules in tumor
microenvironments due to the leaky vasculature.
[0083] For example, in certain embodiments, an ultra-small (e.g.,
having a diameter range from 5 nm to 10 nm), was tested in humans
as is described in U.S. Publication No. 2014/0248210 A1, which is
hereby incorporated by reference in its entirety. In this example,
five patients had no adverse events and the agent was well
tolerated over the study period. Pharmacokinetic behavior,
expressed as the percentage of the injected dose per gram of tissue
(% ID/g), versus time post-injection and the corresponding mean
organ absorbed doses, were comparable to those found for other
commonly used diagnostic radiotracers. Serial PET imaging of this
representative patient showed progressive loss of presumed blood
pool activity from major organs and tissues, with no appreciable
activity seen by 72-hour post-injection (p.i.). Whole-body
clearance half-times in these patients were estimated to range from
13-21 hours. Interestingly, there was no notable localization in
the liver, spleen, or bone marrow, in contrast to many hydrophobic
molecules, proteins, and larger particle platforms (greater than 10
nm). Although patients were pretreated with potassium iodide (KI)
to block thyroid tissue uptake, a higher average absorbed thyroid
dose was obtained in this patient relative to other tissues.
Particles were also primarily excreted by the kidneys, with both
kidney and bladder wall (after thyroid and tumor, see below),
demonstrating one of the highest % ID/g values by 72 hrs p.i.; as
is often the case for renally excreted radiopharmaceuticals, the
bladder wall received a higher average absorbed dose than other
major organs and tissues. These findings highlight the fact that
renal, rather than hepatobiliary, excretion is the predominant
route of clearance from the body.
[0084] Epidermal growth factor receptor (EGFR) is used for targeted
therapy. EGFR mutations resulting in constitutive activation have
been found in 10-35% of metastatic non-small cell lung cancer
(NSCLC), and while EGFR inhibitors are effective for systemic
disease, control of brain metastases remains limited by drug
delivery. EGFR mutations are also found in 40-50% of primary
glioblastoma multiforme (GBM)--two prevalent forms of brain cancer.
While EGFR-tyrosine kinase inhibitors (TKIs), such as gefitinib,
have shown promise in preclinical settings, they have demonstrated
to be largely ineffective in brain cancer patients, likely due to
poor tissue or central nervous system (CNS) penetration and
dose-limiting toxicity.
[0085] Gefitinib binds and inhibits the kinase domain active site
of EGFR. To utilize gefitinib in the context of NDCs, it is
important to incorporate a chemically reactive group that does not
significantly perturb drug binding to the kinase domain. X-ray
crystallographic and SAR studies revealed that replacing the
morpholino-group with an amine does not significantly alter drug
activity but provides the needed chemical functionality (amine) for
modification and eventual covalent attachment to the C dot or C'
dot (FIG. 1A).
Experimental Examples
[0086] One example demonstrates exemplary synthesis of nanoparticle
drug conjugates (e.g., silica-based nanoparticle platform with
covalently attached drug molecules) and their characterization and
preliminary biological evaluations.
[0087] With the commercial availability of des-morpholino-gefitinib
(dMG), the desired aminopropyl-dMG (APdMG) was obtained through a
nucleophilic substitution (e.g., in one step) of Boc protected
amino propyl bromide, followed by acid deprotection (FIG. 1A, FIG.
10 (Scheme 1)). Additionally, the gefitinib analogue 2, which is
described in further detail below, was readily obtained from 1 by
coupling Fmoc-dPEG2-COOH, with a subsequent base deprotection step
(FIG. 1A, FIG. 11 (Scheme 2)). To ensure that APdMG 1 and
dPEG.sub.2APdMG 2 have retained activity against EGFR, H1650 cells
were treated with the compounds and analyzed by western blot to
assess phospho-Tyr168 levels in EGFR. The H1650 cells are a model
human tumor-derived non-small-cell lung cancer (NSCLC) line
(bronchioalveolar carcinoma), which contain a mutated EGFR (L858R
and .DELTA.E746-A750) resulting in constitutive activity of the
receptor. Both compounds showed effects similar to gefitinib, with
inhibition of phospho-Tyr.sup.168 at 1 and 10 .mu.M concentrations,
while dPEG.sub.2APdMG 2 showed reduced activity.
[0088] Three linker types were investigated for C dot based drug
delivery (FIG. 1B-1D). The three linker types include dipeptide
sequences which utilize proteases for drug release. Proteases
recognize and bind the dipeptide leading to hydrolysis at the
C-terminal end, releasing the drug component from the linker. Two
model proteases were used to evaluate the linker-drug constructs
described here, trypsin and cathepsin B. Trypsin was selected as a
representative serine protease. It is highly active against
peptides containing basic amino acids such as arginine and lysine,
and cleaves C-terminal to these residues. Cathepsin B is a cysteine
protease with more stringent substrate specificity. The minimal
substrate consensus sequence described to date is a dipeptide motif
containing hydrophobic and basic residues. Similar to trypsin,
cathepsin B cleaves C-terminal to the basic amino acid. The
dipeptides phenylalanine-arginine (Phe-Arg) and
phenylalanine-lysine (Phe-Lys) are the trypsin/cathepsin B
recognition motifs for trypsin and cathepsin, and are included in
the linker-drug constructs (FIGS. 1B-D).
[0089] The Phe-Arg-APdMG is an example of an approach for obtaining
a protease sensitive linker-drug construct (FIGS. 2A and 2B). In
such a design, the gefitinib analog 1 is directly attached to the
C-terminus of the dipeptide sequence. Compound 3 was synthesized
using solid phase peptide synthesis (SPPS) methods, followed by
modification of the C-terminus with 2, and a final deprotection
step yielding 3 (FIG. 11 (Scheme 3)).
[0090] Given the close proximity of the drug component to the
dipeptide motif, potential steric problems that could hinder the
enzyme from binding and hydrolyzing the linker-drug were addressed.
To increase the distance between the dipeptide and drug, APdMG 1
was modified to obtain dPEG.sub.2APdMG 2 (FIG. 13, (Scheme 4)). A
coupling reaction between the dipeptide component and
dPEG.sub.2APdMG 2, followed by a deprotection step, afforded
Phe-Arg-dPEG.sub.2APdMG 4--a linker drug construct containing a
short PEG spacer of 10 atoms between the Phe-Arg and the gefitinib
analogue.
[0091] To retain the increased spacing between the dipeptide and
drug components without introducing structural changes to APdMG 1,
Phe-Lys-PABC-APdMG 5 was synthesized. This linker incorporates a
self-immolative para-aminobenzyloxy carbamate (PABC) group between
the peptide and drug (FIGS. 1D and 2A-2C). Upon enzymatic
hydrolysis, this group further decomposes into para-aminobenzyl
alcohol and CO.sub.2, thereby releasing the APdMG. Synthesis of
compound 5 begins with Fmoc-Lys(Mtt)-OH (FIG. 13 (Scheme 6)). The
protected amino acid is modified with para-aminobenzyl alcohol
giving Fmoc-Lys(Mtt)-PABA 18. Upon removal of the Fmoc group and
coupling with Fmoc-Phe-OH, the protected dipeptide,
Fmoc-Phe-Lys(Mtt)-PABA19 is formed. The free hydroxyl group of the
-PABA is then activated with para-nitrophenol carbonate chloride
leading to an activated carbonate 20, which is then reacted with
APdMG 1 resulting in compound 21. After a round of deprotection and
coupling, compound 22 was obtained. The final deprotection step
required acidic conditions. However, the para-aminobenzyloxy
carbamate group itself is susceptible to decomposition under such
conditions (e.g., acidic conditions). Sufficiently mild conditions
(e.g., 0.5% TFA) were found to remove the Mtt group from the lysine
and the Mmt group from the terminal thiol while preserving the
linker to afford the desired product 16. The Mtt group masking the
lysine side chain is well suited for this overall synthetic
approach as it is stable in the presence of para-nitrophenol
carbonate chloride but labile for removal under mild acidic
conditions. This is in contrast to the more commonly used
hyper-labile Mmt group for lysine side chain protection, which was
readily removed in the presence of para-nitrophenol carbonate
chloride.
[0092] To evaluate the three linker-drug constructs, compounds 3-5
were subjected to enzymatic hydrolysis (Table 1, FIGS. 3A-3C, 4A
and 4B). The drug-linker constructs were incubated with either
trypsin or cathepsin B and the reaction was monitored by HPLC or
LCMS. Trypsin was active against all three constructs: by 60 min
complete hydrolysis of Phe-Arg-APdMG 3 resulting in APdMG 1 was
observed; only 10 min for complete release of dPEG.sub.2APdMG 2
from Phe-Arg-dPEG.sub.2APdMG 4, and release of APdMG 1 from
Phe-Lys-PABC-APdMG 5. However, when constructs were treated with
cathepsin B, no hydrolysis was observed for Phe-Arg-APdMG 3, while
Phe-Arg-dPEG.sub.2APdMG 4 was completely hydrolyzed leading to the
of release dPEG.sub.2APdMG 2.
[0093] Table 1 below illustrates half lifes obtained by drug
release assay for linker-drug constructs.
TABLE-US-00001 TABLE 1 Trypsin Cathepsin B Substrate t.sub.1/2
.sup.a (min) t.sub.1/2 .sup.a (min) Phe-Arg-APdMG (3) 9 NH
Phe-Arg-dPEG.sub.2APdMG (4) 2 110 Phe-Lys-PABC-APdMG (5) 1 1 NH--no
hydrolysis .sup.a Time when 50% of the drug is released from linker
or particle as determined by HPLC at 348 nm.
[0094] In vitro assays were conducted for compounds 3-5 to obtain
drug release profiles and enzyme mediated hydrolysis of the
constructs was monitored over different time points (FIGS. 4A and
4B). For the Phe-Arg-APdMG 3, 50% of drug APdMG 1 was released in 9
min, while the Phe-Arg-dPEG.sub.2APdMG4 was notably faster with 50%
drug release within 2 min. The compound 5 was also fast, requiring
less than 1 min for 50% drug release. In the presence of cathepsin
B, The Phe-Arg-APdMG 3 proved to be a poor substrate, as no drug
release was observed. For the Phe-Arg-dPEG.sub.2APdMG 4, 50% of
drug was released in 110 min. The Phe-Lys-PABC-APdMG 5 required
<1 min for 50% drug, suggesting it to be a highly efficient
substrate for the enzyme.
[0095] For both trypsin and cathepsin B, the rate of drug release
for the three linker-drug constructs follows the same general
trend: Phe-Lys-PABC-APdMG 5>Phe-Arg-dPEG.sub.2APdMG
4>Phe-Arg-APdMG 3 (fastest to slowest). The results for
Phe-Arg-APdMG 3 and Phe-Arg-dPEG.sub.2APdMG 4 suggest that the
proximity of the drug to the dipeptide unit affects enzyme activity
and drug release. Hydrolysis (drug release) is enhanced when the
spacing (distance) between the drug and dipeptide is increased
through the incorporation of a 10 atom PEG group. This effect is
most prominently observed with cathepsin B, which is unable to
hydrolyze construct 3. However, by incorporating the 10 atom PEG
spacer between the drug and dipeptide 4, hydrolysis and drug
release are observed.
[0096] To prepare NDCs, maleimide functionalized C' dots (C'
dots-(Cy5)-PEG-mal) were synthesized. Silanes modified with the Cy5
fluorophore were prepared and titrated with tetramethylorthosilane
(TMOS) into a dilute solution of NH.sub.4OH (molar ratio
TMOS:Cy5:NH3:H20 is 1:0.001:0.44:1215) and allowed to mix for 24
hours (Urata C, Aoyama Y, Tonegawa A, Yamauchi Y, Kuroda K.
Dialysis process for the removal of surfactants to form colloidal
mesoporous silica nanoparticles. Chem Commun (Camb). 2009;
(34):5094-6) (Yamada H, Urata C, Aoyama Y, Osada S, Yamauchi Y,
Kuroda K. Preparation of Colloidal Mesoporous Silica Nanoparticles
with Different Diameters and Their Unique Degradation Behavior in
Static Aqueous Systems, Chem. Mater. 2012; 24(8): 1462-71.) (Wang
J, Sugawara-Narutaki A, Fukao M, Yokoi T, Shimojima A, Okubo T.
Two-phase synthesis of monodisperse silica nanospheres with amines
or ammonia catalyst and their controlled self-assembly. ACS Appl
Mater Interfaces. 2011; 3(5):1538-44.) This resulted in a Cy5
encapsulated silica particle, the surface of which was further
PEGylated and functionalized with maleimide groups by treatment
with PEG-silane (500 g/mole) (Suzuki K, Ikari K, Imai H. Synthesis
of silica nanoparticles having a well-ordered mesostructured using
a double surfactant system. J Am Chem Soc. 2004; 126(2):462-3.) and
maleimide-PEG-silane (molar ratio PEG-silane:TMOS:mal-PEG-silane of
1:2.3:0.006). After 48 hours, the reaction mixture was dialyzed,
filtered and purified by gel filtration. Nanoparticles were
characterized by fluorescence correlation spectroscopy (FCS),
transmission electron microscopy (TEM), and analytical HPLC for
diameter, morphology, and overall purity, respectively. The
resulting C' dots were less than 10 nm in diameter with narrow
particle size distributions (FIGS. 16A-16D).
[0097] NDCs incorporating the linker-drugs 4 and 5 (e.g., C'
dot-(Cy5)-PEG-Phe-Arg-dPEG.sub.2APdMG (6) and C'
dot-(Cy5)-PEG-Phe-Lys-PABC-APdMG (7)) were obtained by adding
Phe-Arg-dPEG.sub.2APdMG (4) and Phe-Lys-PABC-APdMG (5) to the C'
dots-(Cy5)-PEG-mal to allow the terminal thiols on the constructs
to react with maleimide groups on the particles (Scheme 2). The NDC
products were isolated following purification by gel filtration and
yielding NDCs 6 and 7 and characterized by TEM and HLPC (FIG. 16A
and FIG. 16B). Analytical HPLC was used to assess the presence of
contaminants as well as determine the number of drug molecules per
particle or drug to particle ratio (DPR) (Table 2). The
concentration of gefitinib analogs can be readily measured at 348
nm, while particle concentrations can be obtained at 650 nm, due to
the Cy5 embedded within the C' dots. While the average DPR proved
to be modest, the NDCs exhibited measurable heterogeneity where DPR
estimates ranged from less than 1 to greater than 15. Precipitation
of NDCs were not observed, as might be expected due to the poor
solubility of the gefitinib analogues. FCS was used to assess
changes in the particle size due to linker-drug conjugation. As
shown in Table 2, NDCs showed a minimal increase in diameter over
the base mal-C' dot.
[0098] Table 2 below illustrates a summary of nanoparticle
characterization.
TABLE-US-00002 TABLE 2 DPR Diameter .sup.a Average .sup.b Particle
(nm) (Range) C'dot-(Cy5)-PEG-Mal 6.3 --
C'dot-(Cy5)-PEG-Phe-Arg-dPEG.sub.2APdMG (6) 6.4 5 (1-15)
C'dot-(Cy5)-PEG-Phe-Lys-PABC-APdMG (7) 6.5 2 (1-15) DPR--drug to
particle ratio .sup.a Determined by FCS .sup.b Determined by
HPLC
[0099] Enzyme dependent drug release over time was measured for C'
dot-(Cy5)-PEG-Phe-Arg-dPEG.sub.2APdMG and C'
dot-(Cy5)-PEG-Phe-Lys-PABC-APdMG to obtain in vitro drug release
profiles (FIGS. 6A and 6B). Representative HPLC data demonstrating
drug release with trypsin is shown in FIGS. 5A and 5B. NDCs 6 and 7
were excellent substrates for trypsin, requiring 44 min and 6 min,
respectively, to achieve 50% drug release (FIG. 6A, Table 1). In
the presence of cathepsin B, release kinetics were markedly slower
for both NDCs: 50% of drug release was achieved in 560 min for NDC
6 and 510 min for NDC 7 (FIG. 6B, Table 1). Taken together, the
data demonstrates the accessibility of the linker-drug constructs
on the particle surface, leading to the controlled release of the
drug components.
[0100] The stabilities of NDCs were evaluated in aqueous conditions
under acidic and neutral pH (5.0 and 7.2) at 37.degree. C. Both NDC
6 and 7 exhibited no degradation or drug release for 48 hours, as
measured by HPLC. Thiol-maleimide based conjugations have drawn
scrutiny due to the observed loss of linker drug constructs from
antibody drug conjugates due to possible reverse Michael or thiol
exchange reactions that can occur in vivo. To assess in vitro
stability of the NDCs in the presence of excess thiols, NDC7 was
incubated with 30 mM gluthathione at 37.degree. C. for 48 hours at
pH 7.2. Less than 5% of the linker-drug was separated from the C
dot after 48 hours (Table 4).
[0101] Table 3 below illustrates half lifes obtained by drug
release assay for linker-drug constructs.
TABLE-US-00003 TABLE 3 Trypsin Cathepsin B Substrate t.sub.1/2
.sup.a (min) t.sub.1/2 .sup.a (min)
C'dot-(Cy5)-PEG-Phe-Arg-dPEG.sub.2APdMG (6) 44 560
C'dot-(Cy5)-PEG-Phe-Lys-PABC-APdMG (7) 6 510 .sup.a Time when 50%
of the drug is released from linker or particle. Determined by
HPLC
[0102] Table 4 below illustrates NDC stability data.
TABLE-US-00004 TABLE 4 pH 5.2 .sup.a pH 7.2 .sup.b Glutathione
.sup.c Media Particle 48 hr 48 hr 48 hr 18 hr NDC 6 ~1% ~2% ~5%
<5% NDC 7 ~6% ~2% ~4% <1% .sup.a 25 mM sodium acetate buffer
.sup.b 50 mM phosphate buffer .sup.c 10 mM glutathione (reduced) in
50 mM phosphate buffer .sup.d DEM, serum free, 18 hrs after cell
treatment
[0103] The biological activities of C'
dot-(Cy5)-PEG-Phe-Arg-dPEG.sub.2APdMG and C'
dot-(Cy5)-PEG-Phe-Lys-PABC-APdMG were assessed by treatment of
H1650 cells followed by western blot detection of
phospho-Tyr.sup.168 in EGFR and compared with gefitinib. Serum
starved cells were incubated with each compound over a period of 18
hours, then subject to EGF stimulation. The gefitinib control
exhibited a dose dependent decrease in Tyr.sup.168 phosphorylation
of EGFR with complete ablation at 1 .mu.M (FIG. 7). NDCs 6 and 7
also showed dose dependent inhibition; cells treated with NDC 6
showed detectable levels of phospho-Tyr.sup.168 at 10 NM. In
contrast NDC7 exhibited good activity, with significant reduction
of phospho-Tyr.sup.168 at 100 nM, and complete ablation at NDC
concentrations of 1 .mu.M. Given the possibility that premature
drug release can occur and lead to the observed decreases in
phospho-Tyr.sup.168EGFR, the stability of the NDCs used in these
assays were monitored. An aliquot of the media with NDC 6 or 7 (10
.mu.M) used for treating the H1650 cells for 18 hours was analyzed
by HPLC. Both particles proved to be stable under these conditions
as no free drug was detected in the media and NDCs were intact
(Table 3). In addition to the NDCs 6 and 7, incorporation of a
secondary imaging modality for eventual in vivo studies was
investigated. A linker-drug construct with
Phe-Arg-dPEG.sub.2-D-Tyr-aminopropyl-dMG was synthesized
incorporating a D-tyrosine residue with the drug component for
attaching a radiolabel (compounds 23 and 24). The NDC C'
dot-(Cy5)-PEG-Phe-Arg-dPEG.sub.2-D-Tyr-APdMG was prepared, and
successfully radioiodinated with .sup.131I at >90% radiochemical
purity (FIG. 8). Reagents:
[0104] Solvents and reagents purchased from commercial sources were
used without further purification. Acetonitrile, diethyl ether,
dimethylformamide (DMF), ethyl acetate, hexanes,
hexafluoroisopropanol (HFIP), methanol, methylene chloride (DCM),
and trifluoroacetic acid (TFA) were obtained from Fisher.
Dimethylsulfoxide (DMSO), diisopropylethylamine (DIEA),
triethylamine (TEA), potassium carbonate,
N-(tert-butyloxycarbonyl)-aminopropylbromide,
(3-aminopropyl)triethoxysilane (APTES),
(3-mercaptopropyl)trimethoxysilane (MPTMS), tetramethyl
orthosilicate (TMOS), bovine trypsin, and were purchased from
Sigma-Aldrich. O-Des-morpholinopropyl gefitinib was obtained from
Toronto Research Chemicals (TRC).
2-(7-Aza-1H-benzotriazole-1-yl)-1,1,3,3-tetramethyluronium
hexafluorophosphate (HATU) was purchased from Genescript.
Chlorotrityl-resins and protected amino acids (Fmoc-Arg-OH,
Fmoc-Lys(Mtt)-OH, Fmoc-Phe-OH) were obtained from EMD Chemicals.
Fmoc-N-dPEG.sub.2OH, Mmt-S-dPEG.sub.8-OH, mal-dPEG.sub.12-NHS were
purchased from Quanta Biosciences. Cy5 maleimide and Superdex 200
(prep grade) was obtained from GE Life Sciences. DMSO-d and
CDCl.sub.3 were purchased from Cambridge Isotopes. Solid-phase
synthesis was conducted in polypropylene fritted syringes from
Torviq. Silica, TLC plates, 4 g, 12 g, 24 g, and 40 g RediSep Rf
normal phase cartridges were obtained from Teledyne ISCO.
Flash Chromatography:
[0105] Normal phase (silica gel) purifications were conducted on a
Teledyne ISCO CombiFlash Rf using 4 g, 12 g, 24 g, and 40 g
cartridges.
Analytical HPLC:
[0106] Samples were run on a Waters Alliance HPLC System or
Autopure LCMS System (2767 Sample Manager, 2996 Photodiode Array
Detector, 2420 ELS Detector, Micromass ZQ, 2525 Binary Gradient
Module, Column Fluidics Organizer, 515 HPLC Pump, Pump Control
Module II) using a linear gradient of 5-95% acetonitrile in water
(0.5% TFA) for 10 minutes at 1.2 mL/min, on either a C4 or C18
4.6.times.50 mm reversed phase XBridge analytical column (Waters).
Samples were analyzed at either 348 nm or 650 nm.
Preparative HPLC:
[0107] Samples were purified on either a Waters Preparative System
(2996 Photodiode Array Detector, 2545 Binary Gradient Module) or
Autopure LCMS System using a linear gradient of 5-95% acetonitrile
in water (0.5% TFA) for 30 minutes at 20 mL/min on a C18
19.times.150 mm reversed phase XBridge preparative column (Waters).
Samples were analyzed at either 220 or 348 nm.
Nuclear Magnetic Resonance (NMR);
[0108] .sup.1H-NMR and .sup.13C-NMR data were obtained on a Bruker
Ultrashield 500 Plus. Drug Release Assays with Trypsin:
[0109] Assays were conducted in 25 mM phosphate buffer (pH 7.2) at
37.degree. C., with 25 .mu.M NDC (e.g., 6 or 7) or free linker-drug
(e.g., 3, 4, or 5) and 200 nM trypsin. For analysis, 70 .mu.L
portions were removed and quenched with acid (HCl) at specified
time points (e.g., 5, 15, 30, 60, 120 minutes or longer) then run
on HPLC/LCMS. NDCs were stored in water at 4.degree. C. Trypsin
stocks were prepared as follows: 1 mg of trypsin was dissolved in 1
mL water, aliquoted, then immediately flash frozen and stored at
-80.degree. C. for up to four weeks. Enzyme activity was tested
prior to drug release assay using the substrate
Z-Arg-Arg-para-nitro-aniline. The % Free Drug (FIG. 3 and S3) is
the quantity of free drug divided by the initial quantity of drug
loaded for the linker-drug construct or NDC. The quantity of free
drug is determined by area of the HPLC peak corresponding to the
released drug at 348 nm. The quantity of drug loaded is the area of
the HPLC peak, at 348 nm, for the linker-drug construct or NDC
prior to enzyme treatment. As the C'dot-(Cy5)-PEG-mal has
background absorbance at 348 nm, a background subtraction for the
NDC is necessary. All buffers and solutions were prepared using
ultra-pure water (18 M.OMEGA.-cm resistivity).
Drug Release Assays with Cathepsin B:
[0110] Assays were conducted in 25 mM sodium acetate buffer (pH
5.0) at 37.degree. C., with 25 .mu.M NDC (e.g., 6 or 7) or free
linker-drug (e.g., 3, 4, or 5) and 200 nM cathepsin B. No DTT was
used for this assay. For analysis, 70 .mu.L portions were removed
and quenched with acid (HCl) at specified time points (e.g., 5, 15,
30, 60, 120 minutes or longer) then run on HPLC/LCMS. NDCs were
stored in water at 4.degree. C. Cathepsin B stocks were prepared as
follows: 1 mg of cathepsin B was dissolved in 1 mL 50 mM sodium
acetate and 2.5 mM EDTA, aliquoted, then immediately flash frozen
and stored at -80.degree. C. for several weeks. Enzyme activity was
tested prior to drug release assay using the substrate
Z-Arg-Arg-para-nitro-aniline. The % Free Drug (FIGS. 4A, 4B, 6A and
6B) is the quantity of free drug divided by the initial quantity of
drug loaded for the linker-drug construct or NDC, as described in
the previous paragraph. All buffers and solutions were prepared
using ultra-pure water (18 MQ-cm resistivity).
NDC Stability Assays:
[0111] Assays were conducted in either 25 mM sodium acetate buffer
(pH 5.0) or 50 mM phosphate buffer (pH 7.2) with 7.5 .mu.M NDC
(e.g., 6 or 7) and incubated at 37.degree. C. for up to 48 hours.
10 mM Glutathione (reduced) in phosphate buffer (pH 7.2) was also
evaluated. 20 .mu.L aliquots were then analyzed by HPLC. For one
experiment, after H1650 cells were treated with 10 .mu.M NDC (see
the phosphoEGFR assay below) in serum free DEM for 18 hours, the
media was recovered and analyzed by HPLC.
PhosphoEGFR Assay with H1650 Cells:
[0112] H1650 cells were seeded (1.5 million cells) in 6-well plates
with 2 ml of 10% FBS DEM medium and grown for 24 hrs. Cells were
washed with 1 mL of serum free DEM medium, then incubated with
gefitinib or NDCs at indicated concentrations overnight (18 hrs).
Cells were then treated with 50 ng/mL EGF for 5 minutes, then
washed with 1 mL of PBS. Trypsin (0.5 ml, 0.25%) was added to each
well, and incubated until cells detached (.about.5 min). 1 mL of
10% FBS DEM medium was added to wells, and cells were transferred
to 15 mL conical tubes containing 10 mL of 10% FBS DEM medium.
Cells were spun down at 3000 rpm for 5 minutes at 4.degree. C. The
cell pellets were washed with 1 mL cold PBS, transferred to 1.5 mL
tubes, and spun down. PBS was decanted and 70 .mu.L of RIPA
(containing protease and phosphatase inhibitors) was added to the
pellet, titurated, and incubated for 10 minutes on ice. Tubes were
spun at maximum speed for 10 minutes at 4.degree. C. Lysate was
transferred to new 1.5 ml tubes and stored at -80.degree. C.
Protein concentrations were determined by the Bradford assay.
Western blots were run on a Life Technologies apparatus, using
Novex 8% tris-glycine gels (1.5 mm.times.15 wells), tris-glycine
SDS running buffer, NuPAGE transfer buffer, 0.1% Tween-20 in
1.times.TBS washing buffer, and 5% milk in the washing buffer as
the blocking buffer. Primary antibodies were applied as follows:
anti-phosphorylated-EGFR (pEGFR, Tyr.sup.1068) (1:1000 dilution;
Cell Signaling), anti-EGFR (D38B1) (1:5000 dilution; Cell
Signaling), monoclonal anti-.beta.-actin clone AC-15 (1:5000
dilution; Sigma-Aldrich). Secondary antibodies applied were goat
anti-mouse IgG-HRP (1:10000 dilution; Santa Cruz Biotechnology) and
goat anti-rabbit IgG-HRP (1:5000 dilution; Santa Cruz
Biotechnology).
Preparation of O-des-Morpholino-gefitinib, dMG (8, in FIG. 12
(Scheme 3))
[0113] Compound was obtained commercially.
[0114] .sup.1H-NMR (500 MHz, DMSO-d6): .delta. 9.69 (s, 1H), 9.47
(s, 1H), 8.48 (s, 1H), 8.22 (dd, J=6.9, 2.7 Hz, 1H), 7.84 (ddd,
J=9.1, 4.4, 2.7 Hz, 1H), 7.78 (s, 1H), 7.41 (t, J=9.1 Hz, 1H), 7.22
(s, 1H), 3.98 (s, 3H). .sup.13C-NMR (500 MHz, DMSO-d6): .delta.
155.83, 153.91, 151.89, 146.73, 146.20, 122.74, 121.69, 116.50,
116.33, 109.51, 107.18, 105.25, 55.92. ESI-MS (m/z) for
C.sub.15H.sub.11ClFN.sub.3O.sub.2 (exact mass 319.1): [M+H].sup.+
calc. 320.1, obs. 320.2.
Synthesizing N-(tert-Butyloxycarbonyl)-aminopropyl-dMG (9, in FIG.
12 (Scheme 3))
[0115] 500 mg of compound 8 was dissolved in 100 mL of anhydrous
DMF. K.sub.2CO.sub.3 (mg, mmol) was added to the solution. The
reaction proceeded at 60.degree. C. for 16 hrs and checked by TLC
and/or HPLC. The solvent was removed in vacuo leaving a brown oil,
which was flash purified on a 24 g RediSep Rf normal phase
cartridge using a linear gradient of DCM to 20% MeOH in DCM. The
final product was isolated as a white solid (312 mg, 62%
yield).
[0116] .sup.1H-NMR (500 MHz, DMSO-d6): .delta. 9.57 (s, 1H), 8.49
(s, 1H), 8.12 (dd, J=6.8, 2.7 Hz, 1H), 7.81 (m, 1H), 7.44 (t, J=9.1
Hz, 1H), 7.20 (s, 1H), 6.92 (t, J=5.7 Hz, 1H), 4.17 (t, J=6.0 Hz,
2H), 3.95 (s, 3H), 3.15 (q, J=6.5 Hz, 2H), 1.95 (p, J=6.5 Hz, 2H),
1.38 (s, 9H). .sup.13C-NMR (500 MHz, DMSO-d6): .delta. 156.01,
155.59, 154.39, 152.61, 146.92, 123.40, 122.29, 118.62, 116.54,
116.37, 107.23, 102.59, 77.51, 66.69, 55.84, 37.22, 35.75, 28.95,
28.22. ESI-MS (m/z) for C.sub.23H.sub.26ClFN.sub.4O.sub.4 (exact
mass 476.2): [M+H].sup.+ calc. 477.2, obs. 477.3.
Preparation of Aminopropyl-O-des-morpholino-gefitinib, APdMG (1, in
FIG. 1A and FIG. 12 (Scheme 3))
[0117] Compound 9 (100 mg, 0.21 mmol) was treated with 1 mL
TFA:water (9:1) for 30 min. The TFA:water was removed in vacuo,
leaving a light yellow oil. The oil was washed with diethyl ether,
then dissolved in a solution of water:acetonitrile (1:1), frozen
and lyophilized. A tan solid was obtained (TFA salt, 98 mg, 95%
yield).
[0118] .sup.1H-NMR (500 MHz, DMSO-d6): .delta. 10.73 (s, 1H), 8.80
(s, 1H), 8.03 (s, 1H), 8.05-8.00 (m, 1H), 7.88 (s, 3H), 7.72 (ddd,
J=9.0, 4.3, 2.6 Hz, 1H), 7.54 (t, J=9.0 Hz, 1H), 7.35 (s, 1H), 4.27
(t, J=5.9 Hz, 2H), 4.00 (s, 3H), 3.04 (p, J=6.7, 6.3 Hz, 2H), 2.13
(dt, J=12.2, 6.0 Hz, 2H). .sup.13C-NMR (500 MHz, DMSO-d6): .delta.
158.02, 148.80, 116.96, 116.79, 107.60, 103.66, 66.17, 56.42,
36.39, 26.59. ESI-MS (m/z) for C.sub.18H.sub.18ClFN.sub.4O.sub.2
(exact mass 376.1): [M+H].sup.+ calc. 377.1, obs. 377.2.
Preparation of
9-Fluorenylmethoxycarbonyl-N-amido-dPEG.sub.2-aminopropyl-dMG,
Fmoc-dPEG.sub.2APdMG (10, in FIG. 13 (Scheme 4))
[0119] A solution containing dPEG.sub.2APdMG 2 (25 mg, 0.05 mmol,
TFA salt) and Fmoc-N-amido-dPEG.sub.2-COOH (20 mg, 0.05 mmol) in
DMF (500 .mu.L) was prepared. DIEA (19 mg, 0.15 mmol, 26 .mu.L) was
added followed by a solution of HATU (19 mg, 0.05 mmol) in DMF (100
.mu.L). The reaction proceeded for 30 min at room temp, and
determined complete by LCMS. The volume was reduced in vacuo, and
purified by silica gel chromatography using a gradient of ethyl
acetate and 10% methanol in ethyl acetate. Fractions were
collected, pooled and solvent removed in vacuo. The isolated
product was a white solid (84% yield).
[0120] .sup.1H-NMR (500 MHz, DMSO-d6): .delta. 9.55 (d, J=10.7 Hz,
1H), 8.51 (d, J=2.4 Hz, 1H), 8.18-8.07 (m, 1H), 7.96 (t, J=5.5 Hz,
1H), 7.87 (d, J=7.6 Hz, 2H), 7.83-7.76 (m, 2H), 7.67 (d, J=7.5 Hz,
2H), 7.49-7.36 (m, 3H), 7.31 (td, J=7.5, 1.2 Hz, 3H), 7.21 (s, 1H),
4.28 (d, J=6.9 Hz, 2H), 4.24-4.10 (m, 3H), 3.94 (s, 3H), 3.60 (t,
J=6.4 Hz, 2H), 3.46 (s, 4H), 3.36 (t, J=6.0 Hz, 2H), 3.27 (q, J=6.6
Hz, 2H), 3.10 (q, J=5.9 Hz, 2H), 2.32 (t, J=6.5 Hz, 2H), 1.97 (p,
J=6.5 Hz, 2H). .sup.13C-NMR (500 MHz, CDCl.sub.3): .delta. 170.08,
143.85, 127.54, 126.98, 125.10, 120.05, 102.60, 69.42, 69.04,
66.78, 66.58, 55.87, 46.69, 40.01, 39.94, 39.85, 39.77, 39.68,
39.60, 39.51, 39.43, 39.35, 39.25, 39.18, 39.07, 39.01, 36.16,
35.69, 28.67, 0.08. ESI-MS (m/z) for
C.sub.40H.sub.41ClFN.sub.5O.sub.7 (exact mass 757.27): [M+H].sup.+
calc. 758.3, obs. 758.4.
Preparation of Amino-dPEG.sub.2-aminopropyl-dMG, dPEG.sub.2APdMG
(2, in FIG. 1A and FIG. 13 (Scheme 4))
[0121] Compound 10 (10 mg, 0.013 mmol) was dissolved in 30%
piperidine in DMF (1 mL) and allowed to react for 15 min at room
temperature. The solvent was removed in vacuo, dissolved in
water/acetonitrile and purified by reversed phase (C18) HPLC. The
product was recovered as a white powder (7 mg, 80% yield).
[0122] .sup.1H-NMR (500 MHz, DMSO-d6): .delta. 10.66 (s, 1H), 8.78
(s, 1H), 8.05-7.97 (m, 3H), 7.80 (s, 3H), 7.72 (ddd, J=9.0, 4.3,
2.6 Hz, 1H), 7.54 (t, J=9.1 Hz, 1H), 7.32 (s, 1H), 4.20 (t, J=6.1
Hz, 2H), 4.00 (s, 3H), 3.65-3.48 (m, 7H), 3.27 (q, J=6.6 Hz, 2H),
2.96 (q, J=5.5 Hz, 2H), 2.34 (t, J=6.5 Hz, 2H), 1.98 (t, J=6.5 Hz,
2H). .sup.13C-NMR (500 MHz, DMSO-d6): .delta. 116.96, 69.55, 69.29,
66.73, 66.61, 56.38, 38.57, 36.03, 35.63, 28.58. ESI-MS (m/z) for
C.sub.25H.sub.31ClFN.sub.5O.sub.5 (exact mass 535.20): [M+H].sup.+
calc. 536.2, obs. 536.3.
Preparation of Boc-N-amino-(dPEG.sub.2).sub.3-Phe-Arg(Pbf)-OH (11,
in FIG. 14 (Scheme 5))
[0123] Chlorotrityl resin (100 mg, 0.1 mmol, 1 mmol/g) was
transferred into a fritted syringe reaction vessel and suspended in
2 mL anhydrous DCM for 10 min. The solvent was dispensed, and a
solution of DIEA in anhydrous DCM followed by a solution of
Fmoc-Arg(Pbf)-OH (97.5 mg, 1.5 eq) in anhydrous DCM were drawn into
the syringe; and agitated for 40 min. The solution was dispensed
and the resin washed for 2 min, 2.times. with DCM, then 2.times.
with DMF. Standard solid phase peptide synthesis procedures were
the carried out to obtain the final peptide. In short Fmoc
deprotections were accomplished by washing the resin 2.times. using
30% piperidine/DMF (1 mL) for 10 min. This was followed by DMF (1
mL) washes, 4.times. for 2 min each. Coupling reactions were
carried out at room temp using a 3 eq excess of protected amino
acid (in 2 mL DMF), 9 eq excess of DIEA (120 mg, 0.9 mmol, 160
.mu.L, in 1 mL DMF), 3 eq excess of HATU (mmol, mg, .mu.L, in 2 mL
DMF), added to the syringe in that order, and shaken for 1 hr. This
was followed by DMF (1 mL) washes, 4.times. for 2 min each.
Fmoc-Phe (116 mg) was added, followed by three residues of
Fmoc-N-dPEG.sub.2-OH (120 mg). After completion of the sequence,
final Fmoc deprotection and washes, BOC anhydride (mmol, mg) and
DIEA (mmol, mg, .mu.L) in 2 mL of DMF were used to cap the
N-terminal amine. The peptide-resin was washed with DMF (1 mL, 2
min, 2.times.), then DCM (1 mL, 2 min, 4.times.). The protected
peptide product was then cleaved off of the resin by adding 50%
HFIP in DCM (2 mL) to the syringe and shaking for 1 hr at room
temp. The crude peptide was then purified by reversed phase HPLC.
ESI-MS (m/z) for C.sub.54H.sub.86N.sub.8O.sub.17S (exact mass
1150.56): [M+H].sup.+ calc. 1151.6, obs. 1151.7.
Preparation of Boc-N-amido-(dPEG.sub.2).sub.3-Phe-Arg(Pbf)-APdMG
(12, in FIG. 14 (Scheme 5))
[0124] A solution containing compound 11 (23 mg, 0.02 mmol, 1 eq)
and APdMG 1 (9 mg, 0.024 mmol, 1.2 eq) in DMF (1 mL) was prepared.
To this DIEA (10 mg, 0.08 mmol, 14 .mu.L, 4 eq) was added followed
by HATU (9 mg, 0.024 mmol, 1.2 eq). The reaction was monitored by
HPLC, and completed within 30 minutes. The solvent was removed in
vacuo, then resuspended in DCM. The DCM solution was washed with
water 4.times., then evaporated leaving a tan oil. ESI-MS (m/z) for
C.sub.72H.sub.102ClFN.sub.12O.sub.18S (exact mass 1508.68):
[M+H].sup.+ calc. 1509.7, obs. 1509.7; [M+2H].sup.2+ calc. 755.4,
obs. 755.0.
Preparation of
Boc-N-amido-(dPEG.sub.2).sub.3-Phe-Arg(Pbf)-dPEG.sub.2APdMG (13, in
FIG. 14 (Scheme 5))
[0125] A solution containing compound 11 (30 mg, 0.026 mmol, 1 eq)
and dPEG.sub.2APdMG 2 (18 mg, 0.034 mmol, 1.3 eq) in DMF (1 mL) was
prepared. To this DIEA (14 mg, 0.1 mmol, 18 .mu.L, 4 eq) was added
followed by HATU (13 mg, 0.034 mmol, 1.3 eq). The reaction was
monitored by HPLC, and completed within 30 minutes. The solvent was
removed in vacuo, then resuspended in DCM. The DCM solution was
washed with water 4.times., then evaporated leaving a tan oil.
ESI-MS (m/z) for C.sub.79H.sub.115ClFN.sub.13O.sub.21S (exact mass
1667.77): [M+2H].sup.2+ calc. 834.9, obs. 834.7.
Preparation of H.sub.2N-(dPEG.sub.2).sub.3-Phe-Arg-APdMG (14, in
Scheme 6)
[0126] TFA/water (9:1, 1 mL) was added compound 12 (.about.0.02
mmol from previous step) and left at room temperature for 1 hour.
The reaction was evaporated then dissolved in ACN/water, frozen and
lyophilized leaving a tan solid. The crude material was purified by
reversed phase HPLC. The final product was left as a white solid
(14 mg). ESI-MS (m/z) for C.sub.54H.sub.78ClFN.sub.12O.sub.13
(exact mass 1156.55): [M+H].sup.+ calc. 1157.6, obs. 1157.8;
[M+2H].sup.2+ calc. 579.3, obs. 579.1.
Preparation of
H.sub.2N-(dPEG.sub.2).sub.3-Phe-Arg-(dPEG.sub.2)-APdMG (15, in FIG.
14 (Scheme 5))
[0127] TFA/water (9:1, 1 mL) was added compound 13 (.about.0.026
mmol from previous step) and left at room temp for 1 hour. The
reaction was evaporated then dissolved in ACN/water, frozen and
lyophilized leaving a tan solid. The crude material was purified by
reversed phase HPLC. The final product was left as a white solid
(24 mg). ESI-MS (m/z) for C.sub.61H.sub.91ClFN.sub.13O.sub.16
(exact mass 1315.64): [M+H].sup.+ calc. 1316.7, obs. 1316.5;
[M+2H].sup.2+ calc. 658.6, obs. 658.5.
Preparation of
S-Acetyl-mercaptoacetamido-(dPEG.sub.2).sub.3-Phe-Arg-APdMG (16, in
FIG. 14 (Scheme 5))
[0128] A solution containing compound 14 (5 mg, 0.004 mmol, 1 eq)
and DIEA (1.5 mg, 0.012 mmol, 2 .mu.L, 3 eq) in DMF (200 .mu.L) was
prepared. SAMA-OPfp (2 mg, 0.006 mmol, 1.5 eq) in DMF (100 .mu.L)
was then added to the solution, and allowed to react for 1 hour.
The solvent was removed in vacuo then purified by reversed phase
HPLC. 3 mg of a white solid was recovered. ESI-MS (m/z) for
C.sub.61H.sub.91ClFN.sub.13O.sub.16 (exact mass 1315.64):
[M+H].sup.+ calc. 1316.7, obs. 1316.5; [M+2H].sup.2+ calc. 658.6,
obs. 658.5.
Preparation of
S-Acetyl-mercaptoacetamido-(dPEG.sub.2).sub.3-Phe-Arg-dPEG.sub.2APdMG
(17, in FIG. 14 (Scheme 5))
[0129] A solution containing compound 15 (5 mg, 0.004 mmol, 1 eq)
and DIEA (1.5 mg, 0.012 mmol, 2 .mu.L, 3 eq) in DMF (200 .mu.L) was
prepared. SAMA-OPfp (2 mg, 0.006 mmol, 1.5 eq) in DMF (100 .mu.L)
was then added to the solution, and allowed to react for 1 hour.
The solvent was removed in vacuo then purified by reversed phase
HPLC. 3 mg of a white solid was recovered. ESI-MS (m/z) for
C.sub.65H.sub.95ClFN.sub.13O.sub.18S (exact mass 1431.63):
[M+2H].sup.2+ calc. 716.8, obs. 716.7.
Preparation of Mercaptoacetamido-(dPEG.sub.2).sub.3-Phe-Arg-APdMG,
Phe-Arg-APdMG (3, in FIG. 1B and FIG. 14 (Scheme 5))
[0130] This step was performed immediately prior to use. 1 mg of
compound 16 was dissolved in 100 .mu.L of water/MeOH (1:1), to
which 2 .mu.L of 1 N NaOH was added. After 15 minutes, 2 .mu.L of 1
M HCl was added to neutralize. The solution was directly used.
ESI-MS (m/z) for C.sub.56H.sub.80ClFN.sub.12O.sub.14S (exact mass
1230.53): [M+H].sup.+ calc. 1231.5, obs. 1231.4; [M+2H].sup.2+
calc. 616.3, obs. 616.3.
Preparation of
Mercaptoacetamido-(dPEG.sub.2).sub.3-Phe-Arg-dPEG.sub.2APdMG,
Phe-Arg-dPEG.sub.2APdMG (4, in FIG. 1C and FIG. 14 (Scheme 5))
[0131] This step was performed immediately prior to use. 1 mg of
compound 17 was dissolved in 100 .mu.L of water/MeOH (1:1), to
which 2 .mu.L of 1 N NaOH was added. After 15 minutes, 2 uL of 1 M
HCl was added to neutralize. The solution was directly used. ESI-MS
(m/z) for C.sub.63H.sub.93ClFN.sub.13O.sub.17S (exact mass
1389.62): [M+H].sup.+ calc. 1390.6, obs. 1390.5; [M+2H].sup.2+
calc. 695.8, obs. 695.7.
Preparation of Fmoc-Lys(Mtt)-PABOH (18, in FIG. 15 (Scheme 6))
[0132] A solution of Fmoc-Lys(Mtt)-OH (748 mg, 1.2 mmol, 1 eq) and
para-amino benzyl alcohol (300 mg, 2.4 mmol, 2 eq) in DMF (5 mL)
was prepared. DIEA (465 mg, 3.6 mmol, 630 .mu.L, 3 eq) was added
followed by a solution of HATU (502 mg, 1.3 mmol, 1.1 eq) in DMF (2
mL). The reaction was complete within 30 minutes and as determined
by HPLC/LCMS. The solvent was partially removed in vacuo, and
extracted with ethyl acetate/water. The ethyl acetate layer was
washed 4.times. with water, then evaporated leading to an orange
solid. The crude material was purified on a 40 g RediSep Rf normal
phase cartridge using a linear gradient of hexane and ethyl
acetate. The final product was isolated as a white solid (850 mg,
97% yield).
[0133] .sup.1H-NMR (500 MHz, CDCl.sub.3): .delta. 7.96 (s, 1H),
7.73 (d, J=7.9 Hz, 2H), 7.54 (d, J=7.5 Hz, 2H), 7.47-7.41 (m, 6H),
7.39-7.20 (m, 12H), 7.18-7.11 (m, 2H), 7.05 (d, J=7.9 Hz, 2H), 5.29
(s, 1H), 4.63 (s, 1H), 4.44 (d, J=6.4 Hz, 2H), 2.28 (s, 3H), 2.11
(t, J=6.9 Hz, 2H), 1.88 (s, 1H), 1.58 (s, 5H), 1.51 (s, 1H), 1.38
(s, 2H). .sup.13C-NMR (500 MHz, CDCl.sub.3): .delta. 146.36,
143.22, 141.32, 135.70, 128.57, 128.52, 128.49, 127.79, 127.74,
127.12, 126.14, 124.92, 120.16, 120.02, 77.27, 77.02, 76.76, 70.62,
64.92, 60.41, 47.16, 43.30, 30.57, 23.43, 21.07, 20.93, 14.21,
0.01. ESI-MS (m/z) for C.sub.48H.sub.47N.sub.3O.sub.4 (exact mass
729.36): [M+H].sup.+ calc. 730.4, obs. 730.2.
Preparation of Fmoc-Phe-Lys(Mtt)-PABOH (19, in FIG. 15, (Scheme
6))
[0134] The Fmoc group was removed from Fmoc-Lys(Mtt)-PABOH 18 (425
mg, 0.6 mmol, 1 eq) using 9 mL of 30% piperidine in DMF for 10
minutes. The solvent was removed in vacuo, and the resulting oil
was resuspended in 10 mL DMF A solution of Fmoc-Lys(Mtt)-OH (748
mg, 1.2 mmol, 1 eq) and para-amino benzyl alcohol (300 mg, 2.4
mmol, 2 eq) in DMF (5 mL) was prepared. DIEA (465 mg, 3.6 mmol, 630
.mu.L, 3 eq) was added followed by a solution of HATU (502 mg, 1.3
mmol, 1.1 eq) in DMF (2 mL). The reaction was complete within 30
minutes and as determined by HPLC/LCMS. The solvent was partially
removed in vacuo, and extracted with ethyl acetate/water. The ethyl
acetate layer was washed 4.times. with water, then evaporated
leading to an orange solid. The crude material was purified on a 40
g RediSep Rf normal phase cartridge using a linear gradient of
hexane and ethyl acetate. The final product was isolated as a white
solid (850 mg, 97% yield).
[0135] .sup.1H-NMR (500 MHz, CDCl.sub.3) .delta. 8.20 (s, 1H), 7.73
(d, J=7.6 Hz, 2H), 7.50 (s, 2H), 7.48-7.34 (m, 8H), 7.34-7.20 (m,
11H), 7.20-7.07 (m, 7H), 7.04 (d, J=8.1 Hz, 2H), 6.28 (s, 1H), 5.22
(s, 1H), 4.62 (s, 2H), 4.43 (dd, J=10.7, 6.7 Hz, 1H), 4.32 (d,
J=11.5 Hz, 1H), 3.05 (s, 2H), 2.27 (s, 3H), 2.11-2.02 (m, 2H), 1.89
(s, 1H), 1.46 (d, J=6.3 Hz, 1H), 1.26 (s, 2H). .sup.13C-NMR (500
MHz, CDCl.sub.3) .delta. 146.35, 141.31, 136.97, 135.70, 129.10,
128.93, 128.57, 128.50, 127.82, 127.74, 127.71, 127.39, 127.12,
126.14, 124.91, 124.84, 120.10, 120.04, 77.28, 77.23, 77.02, 76.77,
70.60, 67.15, 64.96, 54.06, 47.08, 43.35, 31.30, 30.60, 23.52,
20.93. ESI-MS (m/z) for C.sub.57H.sub.56N.sub.4O.sub.5 (exact mass
876.43): [M+H].sup.+ calc. 877.4, obs. 877.3.
Preparation of Fmoc-Phe-Lys(Mtt)-PABC-APdMG (21, in FIG. 15 (Scheme
6))
[0136] Compound 19 (420 mg, 0.5 mmol, 1 eq) was dissolved in
anhydrous DCM (20 mL). Pyridine (216 mg, 2.7 mmol, 5.4 eq) was
added, followed by a solution of 4-nitrophenyl chloroformate (180
mg, 0.9 mmol, 1.8 eq) in anhydrous DCM. The reaction proceeded for
2 hours at room temperature, then checked by HPLC and TLC. The
solvent was removed in vacuo then purified by on a 24 g RediSep Rf
normal phase cartridge using a linear gradient of hexane and ethyl
acetate. The product Fmoc-Phe-Lys(Mtt)-PABC-pNP (20), was isolated
as a yellow solid (360 mg, 70% yield). Fmoc-Phe-Lys(Mtt)-PABC-pNP
(50 mg, 0.05 mmol, 1 eq) was dissolved in anhydrous DCM (3 mL). A
solution of APdMG 1 (25 mg, 0.05 mmol, TFA salt, 1 eq) with DIEA
(65 mg, 0.5 mmol, 90 .mu.L, 10 eq) in anhydrous DCM was then added
to Fmoc-Phe-Lys(Mtt)-PABC-pNP. The reaction proceeded at room
temperature for 4 hours, then checked by HPLC and TLC. The solvent
was removed in vacuo, and the crude material was purified on a 4 g
RediSep Rf normal phase cartridge with a linear gradient of hexane
and ethyl acetate. The final product was isolated as a yellow solid
(38 mg, 60% yield). ESI-MS (m/z) for
C.sub.76H.sub.72ClFN.sub.8O.sub.8(exact mass 1278.51): [M+H].sup.+
calc. 1279.5, obs. 1279.4; [M+2H].sup.2+ calc. 640.3, obs.
640.3.
Preparation of Mmt-S-dPEG.sub.8-Phe-Lys(Mtt)-pABC-dMG (22, in FIG.
15 (Scheme 6))
[0137] 18 mg of compound 21 (0.014 mmol, 1 eq) was deprotected with
2 mL of 30% piperidine in DMF. After 5 minutes the reaction was
confirmed complete by HPLC/LCMS, and the solvent was removed in
vacuo. The resulting oil was dissolved in DMF (0.5 mL), to which
Mmt-S-dPEG.sub.8-COOH (13 mg, 0.017 mmol, 1.2 eq) and DIEA (9 mg,
0.070 mmol, 13 .mu.L, 5 eq) were added. A solution of HATU (6 mg,
0.014 mmol, 1.2 eq) in DMF (200 .mu.L) was prepared and added to
the reaction. After 1 hr, the reaction was deemed complete by
HPLC/LCMS, and solvent was removed in vacuo. The remaining oil was
flash purified on a 4 g RediSep Rf normal phase cartridge using a
linear gradient of DCM to 10% MeOH in DCM. The final product was
isolated as a white solid (23 mg, 92% yield). ESI-MS (m/z) for
C.sub.100H.sub.114ClFN.sub.8O.sub.16S (exact mass 1768.77):
[M+2H].sup.2+ calc. 885.9, obs. 886.0.
Preparation of HS-dPEG.sub.8-Phe-Lys-PABC-aminopropyl-dMG (5, in
FIG. 15 (Scheme 6))
[0138] 10 mg of compound 22 (5.6 .mu.mol) was treated with 2 mL of
0.5% TFA/5% TIS in DCM for 2 hrs, then checked by HPLC/LCMS to
confirm complete deprotection. The solution was removed in vacuo,
and then washed with cold ether, 3.times.. The white solid was
dissolved in water/acetonitrile (1:1), frozen and lyophilized. The
resulting white solid was used without further purification (6 mg,
86% yield). ESI-MS (m/z) for C.sub.60H.sub.82ClFNsO.sub.15S (exact
mass 1240.53): [M+H].sup.+ calc. 1241.5, obs. 1241.6; [M+2H].sup.2+
calc. 621.3, obs. 621.3.
Preparation of the C'dot-(Cy5)-PEG-Maleimide
[0139] A maleimide and NHS ester functionalized polyethylene glycol
(mal-dPEG.sub.12-NHS) was conjugated with aminosilane (APTES) in
DMSO (molar ratio mal-PEG-NHS:APTES:DMSO 1:0.9:60). The reaction
mixture was left under nitrogen at room temperature for 48 hours to
generate silane functionalized mal-dPEG (mal-dPEG-APTES). A
maleimide functionalized Cy5 (mal-Cy5) was reacted with a
thiol-silane (MPTMS) in DMSO (molar ratio Cy5:MPTMS:DMOS
1:25:1150). The reaction was left under nitrogen at room
temperature for 24 hours to generate a silane functionalized Cy5
(Cy5-MPTMS). TMOS and Cy5-MPTMS were then titrated into an ammonia
hydroxide solution (.about.pH 8) (molar ratio TMOS:Cy5:NH3:H2O
1:0.001:0.44:1215). The solution was stirred at 600 rpm at room
temperature for 24 hours to form homogeneous Cy5 encapsulated
silica nanoparticles. The mal-dPEG-APTES and silane functionalized
polyethylene glycol (PEG-silane, MW around 500, Gelest) were then
added into the synthesis solution to PEGylate and
surface-functionalize the particles (PEG-silane:TMOS:mal-PEG-APTES
1:2.3:0.006). The solution was stirred at 600 rpm at room
temperature for 24 hours followed by incubation at 80.degree. C.
for another 24 hours without stirring. The solution was dialyzed in
2000 mL with deionized water for two days (10 k MWCO), filtered
with 200 nm syringe filters, and finally chromatographically
purified (Superdex 200) resulting in the desired mal-C'dots.
Preparation of C'dot-(Cy5)-PEG-Phe-Arg-dPEG-Gly-D-Tyr-APdMG
[0140] The same overall synthetic strategy used to obtain compound
6 was used. The linker-drug construct
Phe-Arg-dPEG.sub.2-Gly-D-Tyr-APdMG (23) was synthesized. (ESI-MS
(m/z) for C.sub.74H.sub.105ClFN.sub.15O.sub.20S (exact mass
1609.71): [M+2H].sup.2+ calc. 805.9, obs. 805.6). This construct
was attached to C'dot-(Cy5)-PEG-mal as described for NDCs 6 and
7.
Preparation of C'dot-(Cy5)-PEG-Phe-Lys-PABC-Gly-D-Tyr-APdMG
[0141] The same overall synthetic strategy used to obtain compound
7 was used. The linker-drug construct Phe-Lys-PABC-Gly-D-Tyr-APdMG
(24) was synthesized. (ESI-MS (m/z) for
C.sub.71H.sub.94ClFN.sub.10O.sub.18S (exact mass 1460.61):
[M+H].sup.+ calc. 1461.6, obs. 1461.3; [M+2H].sup.2+ calc. 731.3,
obs. 731.5). This construct was attached to C'dot-(Cy5)-PEG-mal as
described for NDCs 6 and 7.
Preparation of Radioiodination of
C'dot-(Cy5)-PEG-Phe-Arg-dPEG-Gly-D-Tyr-aminopropyl-APdMG
[0142] Radioiodination was carried out on
C'dot-(Cy5)-PEG-Phe-Arg-dPEG.sub.2-Gly-D-Tyr-APdMG using lodogen
protocols. Iodination reactions were purified on a PD10 column,
then analyzed by GPC (Superdex).
* * * * *
References