U.S. patent application number 15/722436 was filed with the patent office on 2018-04-05 for hollow silica nanospheres and methods of making same.
The applicant listed for this patent is The Regents of the University of California. Invention is credited to Sadik C. Esener, Johan Ulrik Lind, Davorka Messmer, Kristina K.P. Mitchell, William C. Trogler, Jian Yang.
Application Number | 20180092987 15/722436 |
Document ID | / |
Family ID | 40351453 |
Filed Date | 2018-04-05 |
United States Patent
Application |
20180092987 |
Kind Code |
A1 |
Trogler; William C. ; et
al. |
April 5, 2018 |
HOLLOW SILICA NANOSPHERES AND METHODS OF MAKING SAME
Abstract
The disclosure provide hollow nanospheres and methods of making
and using the same. The methods and compositions of the disclosure
are useful for drug delivery and gene transfer.
Inventors: |
Trogler; William C.; (Del
Mar, CA) ; Esener; Sadik C.; (Solana Beach, CA)
; Messmer; Davorka; (San Diego, CA) ; Lind; Johan
Ulrik; (Copenhagen E., DK) ; Mitchell; Kristina
K.P.; (San Diego, CA) ; Yang; Jian; (San
Diego, CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
The Regents of the University of California |
Oakland |
CA |
US |
|
|
Family ID: |
40351453 |
Appl. No.: |
15/722436 |
Filed: |
October 2, 2017 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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14981748 |
Dec 28, 2015 |
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15722436 |
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13866940 |
Apr 19, 2013 |
9220685 |
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14981748 |
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12673224 |
Feb 12, 2010 |
8440229 |
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PCT/US08/72972 |
Aug 13, 2008 |
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13866940 |
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60955678 |
Aug 14, 2007 |
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61034468 |
Mar 6, 2008 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61K 9/5192 20130101;
A61K 2039/6093 20130101; B82Y 5/00 20130101; A61K 9/0019 20130101;
A61K 9/1611 20130101; A61K 39/0011 20130101; C01B 33/18 20130101;
Y10T 428/2982 20150115; A61K 47/6925 20170801; A61K 9/2009
20130101; A61K 2039/53 20130101; A61P 35/00 20180101; A61K 9/5115
20130101; A61K 47/6923 20170801; Y10S 977/773 20130101; C12N 15/87
20130101; A61K 47/59 20170801; A61K 47/6455 20170801; A61K 49/183
20130101; A61K 49/04 20130101; A61P 37/04 20180101; A61K 9/14
20130101; A61K 48/0041 20130101; C01B 33/12 20130101 |
International
Class: |
C12N 15/87 20060101
C12N015/87; A61K 9/00 20060101 A61K009/00; A61K 9/14 20060101
A61K009/14; C01B 33/18 20060101 C01B033/18; C01B 33/12 20060101
C01B033/12; B82Y 5/00 20110101 B82Y005/00; A61K 49/18 20060101
A61K049/18; A61K 49/04 20060101 A61K049/04; A61K 48/00 20060101
A61K048/00; A61K 39/00 20060101 A61K039/00; A61K 9/51 20060101
A61K009/51 |
Goverment Interests
STATEMENT REGARDING FEDERAL SPONSORED RESEARCH
[0002] This invention was made with government support under
CA119335 awarded by National Institutes of Health. The government
has certain rights in the invention.
Claims
1. A hollow silica nanoparticle for imaging tissue, comprising: a
shell structure including silica and having a hollow interior,
wherein the shell structure is porous; and a biocompatible coating
on an outer surface of the shell structure.
2. The hollow silica nanoparticle of claim 1, wherein the shell
structure includes a spherical shape.
3. The hollow silica nanoparticle of claim 1, wherein the hollow
silica nanoparticle includes a diameter in a range of 10 nm to 1000
nm.
4. The hollow silica nanoparticle of claim 1, wherein the shell
structure includes a diameter in a range of 40 nm to 500 nm.
5. The hollow silica nanoparticle of claim 1, wherein the shell
structure includes a thickness in a range of 3 nm to 5 nm.
6. The hollow silica nanoparticle of claim 1, wherein the shell
structure is formed of a uniform silica material layer having a
plurality of pores distributed over the shell structure.
7. The hollow silica nanoparticle of claim 6, wherein the shell
structure is formed by deposition of a silica compound on a
functionalized template particle that is removed to create the
hollow interior within the uniform silica material layer, wherein
the uniform silica material layer is able to withstand collapsing
upon itself upon removal of the template particle.
8. The hollow silica nanoparticle of claim 1, wherein the
biocompatible coating includes phosphonate polyethylene glycol
(PPEG).
9. The hollow silica nanoparticle of claim 1, further comprising: a
fluorescent dye coupled to the shell structure.
10. The hollow silica nanoparticle of claim 9, wherein the hollow
silica nanoparticle is configured to locate at a tissue in a region
of a living subject's body and to produce a detectable optical
signal responsive to light directed at the tissue based on
fluorescence of the fluorescent dye of the hollow silica
nanoparticle.
11. The hollow silica nanoparticle of claim 1, wherein the hollow
silica nanoparticle is configured to locate at a tissue in a region
of a living subject's body and to produce a detectable signal
responsive to ultrasonic energy directed at the tissue based on a
material property of the hollow silica nanoparticle.
12. The hollow silica nanoparticle of claim 1, wherein the shell
structure further includes a magnetic material.
13. The hollow silica nanoparticle of claim 12, wherein the hollow
silica nanoparticle is configured as an X-ray imaging agent or a
magnetic contrast agent in imaging a tissue of an organism.
14. A nanoparticle device for ultrasound imaging, comprising: a
cluster of monodisperse silica nanoparticles, each comprising a
silica shell structure having a hollow interior, wherein the shell
structure is porous, and a biocompatible coating on an outer
surface of the silica shell structure; and a binder disposed about
the monodisperse silica nanoparticles to form a capsule.
15. The nanoparticle device of claim 14, wherein the binder
includes gelatin.
16. The nanoparticle device of claim 14, wherein the biocompatible
coating includes phosphonate polyethylene glycol (PPEG).
17. The nanoparticle device of claim 14, wherein the silica shell
structure includes a spherical shape.
18. The nanoparticle device of claim 14, wherein each of the
monodisperse silica nanoparticles includes a diameter in a range of
10 nm to 1000 nm.
19. The nanoparticle device of claim 14, wherein the silica shell
structure further includes a magnetic material, and wherein the
cluster of monodisperse silica nanoparticles are configured to
provide an X-ray imaging agent or a magnetic contrast agent when
imaging the tissue of the living subject.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation of U.S. application Ser.
No. 14/981,748, filed Dec. 28, 2015, which is a continuation of
U.S. application Ser. No. 13/866,940, filed Apr. 19, 2013, now U.S.
Pat. No. 9,220,685, which is a continuation of U.S. application
Ser. No. 12/673,224, filed Feb. 12, 2010, now U.S. Pat. No.
8,440,229, which is a U.S. National Stage Application filed under
35 U.S.C. .sctn. 371, and claims priority to International
Application No. PCT/US08/72972, filed Aug. 13, 2008, which
application claims priority under 35 U.S.C. .sctn. 119 to U.S.
Provisional Application Ser. No. 60/955,678, filed Aug. 14, 2007,
and to U.S. Provisional Application Ser. No. 61/034,468, filed Mar.
6, 2008, the disclosures of which are incorporated herein by
reference.
FIELD OF THE INVENTION
[0003] The disclosure relates to nanostructures and methods of
making and using the same. More particularly, the disclosure
provides hollow nanospheres useful for drug delivery, imaging, gene
transfer and sensing.
BACKGROUND
[0004] Traditional drug delivery methods, such as introducing
plasma concentrations of drugs by injection, or inhalation and
ingestion of drugs, can require repeated and relatively greater
dosing, with problematic patient compliance. Chemotherapy, which
applies these methods for cancer treatments, can adversely affect
healthy cells thereby causing serious side effects. Compared with
these methods, a controlled local release system provides the
desired constant drug concentrations at the target specific areas
of the body, lowers systemic drug levels and reduces the potential
for harmful side effects. Many materials have been developed for
drug delivery systems including liposomes, biodegraded polymer
spheres, metal oxides, and other inorganic particles. Another
advanced technology in the medical field is imaging with X-ray or
magnetic contrast reagents.
[0005] Since chemotherapeutic agents have a reduced efficacy in
non-proliferating cells, immunotherapy represents a valuable
treatment option because it is able to eliminate tumor cells
independent of their proliferative state. Tumor associated antigens
have been identified for many tumors and those can serve as target
for the immune system. One of the approaches used to induce immune
responses against cancer cells are DNA vaccines. Injection of
plasmids encoding polypeptides can induce immune responses against
the transgene product, offering a potential means for immunization
without requiring production and purification of complex antigens.
Dendritic cells (DCs) are required to initiate the immune response
to the transgene antigen(s) encoded by such DNA vaccines and
cytotoxic T lymphocytes (CTLs) play a major role in eliminating
malignant cells by specifically recognizing antigenic peptides
presented on MHC class I molecules by dendritic cells (DC). DNA
vaccines although showing some success, are not very efficient and
new approaches are needed to improve efficacy.
SUMMARY
[0006] The disclosure demonstrates that "attachment" of DNA to
hollow silica-NPs will increase DNA uptake by taking advantage the
endocytic capacity of DCs. The data provided herein demonstrate
that DCs readily take up DNA that has been adsorbed to hollow
Silica-NPs and express the encoded transgene. The disclosure
provides a multi-functional nanoparticle vaccine/therapy with good
prospects for treatment and prevention of cancers including
melanoma. The compositions and methods are scalable, single
agent-multi-functional therapeutics. The approach is modular and
useful for delivery of other tumor antigens to treat other
cancers.
[0007] The disclosure provides methods of synthesis of monodisperse
hollow porous nanoparticles and their application in targeted drug
and gene delivery. By examining monodisperse nanoparticles, the
influence of nanoparticle size on cellular uptake and in vivo
transport can be examined, as well as potential imaging
applications. A key aspect is the development of synthetic methods
that permit differential chemical functionalization of the inner
and outer surfaces of the nanoshells. The goals are to attach
targeting ligands (e.g. integrins, targeting peptides, or
antibodies) to the outer shell surface. The inner surface of the
nanoshell will be tailored to have hydrophilic, hydrophobic, and
acid base properties that optimize binding of a specific payload
(e.g. drug, imaging agent, immune stimulant, quantum dot sensor).
These have potential applications in cancer vaccines and drug
therapies. The nanospheres will also be explored in diagnostic
schemes as labeled carriers of PCR primer DNA in the development of
array based analyses for determining genetic mutations in cancer
cells. For surface functionalization of silica and titania
nanospheres, as well as for surface modification of biosensing
chips, air and water stable reagents for self-assembling monolayers
are being prepared.
[0008] The disclosure demonstrates the synthesis of hollow porous
silica and titania nanospheres in the about 20-1000 um range (e.g.,
about 40 nm to about 500 nm range) and shows their use as gene
transfer agents and drug delivery agents to live cells. The data
demonstrate the porosity of the nanoshell walls by heavy element
staining and high resolution transmission electron microscopy. The
cellular distribution of the nanoparticles in vivo was
characterized by fluorescent imaging. The cellular distribution of
nanoparticle payloads can be characterized by using two color
labeling of the particle and payload. Quantum dots or metal
nanoparticles contained within silica nanoshells can be
synthesized. Chemistry techniques can be used to differentially
functionalize the hollow nanoparticle inner and outer surfaces with
hydrophobic and hydrophilic functional groups. In one aspect, the
particles can be loaded and then a defined time release of
doxorubicin from porous hollow nanoparticles can be achieved. Tumor
targeting peptides can be used and attached to the surface of the
nanoparticles for targeting in a cancer models. Fluorescently
labeled nanospheres can be prepared as carriers of PCR primer DNA
into microbubble reactors. In addition phosphonate polyethylene
glycol (PPEG) reagents can be used as a coating for silica and
titania nanospheres for improved in vivo biocompatibility. The
disclosure demonstrates how to generated template synthesis of
monodisperse hollow porous silica and titania nanoshells of 45 nm,
100 nm, 200 nm, and 500 nm diameters and with 3-5 nm thick porous
walls; demonstrated uptake of fluorescently labeled 100 nm silica
shells by live human dendritic cells with no cellular toxicity;
demonstration of quantitative plasmid DNA binding to 100 nm silica
spheres with the use of a cationic surface coating; synthesized
surface functionalized silica nanospheres and demonstrated coupling
of surface amino groups to fluorescent dyes; and synthesized
phosphonate polyethylene glycol (PEG) reagents that allow coating
self-assembled monolayers on silica and titania surfaces for
nonbioadhesive surfaces on biosensor chips. Processing occurs in
aerated aqueous solvents at neutral pH for easy and environmentally
friendly processing.
[0009] The disclosure provides a method to synthesize a hollow
silica nanosphere comprising: (a) synthesizing a precursor of
silica shell by hydrolyzing a silicon-containing compound; (b)
depositing the precursor of silica shell on a template particle
using polyamino acids under neutral condition to give core-shell
spheres; (c) removing the polystyrene core and polyamino acids by
calcination or organic solvent to provide a hollow silica sphere.
In one aspect, the calcination comprises heating the core-shell
sphere to 450.degree. C. In another aspect, the template particles
comprise commercial amine functionalized polystyrene beads. In yet
another aspect, the precursor of silica shell is deposited on the
surface of an amine or carboxylate functionalized polystyrene or
latex bead. The size of the template particle can be from about 40
nm to 1 um. In one aspect the silicon-containing compound is
selected from the group consisting of tetraalkoxysilanes,
trialkoxysilanes, dialkoxysilanes and any combination thereof. In
another aspect the silicon-containing compound is selected from the
group consisting of tetrapropoxysilane, tetraethoxysilane,
tetramethoxysilane and any combination thereof. The
silicon-containing compound can be hydrolyzed in acid solution
(e.g., hydrochloric acid, sulfuric acid, nitric acid or any
combination thereof). The silicon-containing compound can be
hydrolyzed in 0.01M hydrochloric acid aqueous solution. In one
aspect, the final concentration of the silicon-containing compound
in the acids solution is 0.1-10M. In another aspect the final
concentration of the silicon-containing compound in the acids
solution is 1M. In another aspect the polyamino acids include
monopolymer of amino acids with primary amine groups on the
backbone in solid or aqueous solution. In another aspect the
polyamino acids are 0.1% v/w aqueous solution of poly-L-lysine,
poly-L-arginine and polyornithine. In yet another aspect, the
silica shell deposits on the surface of polystyrene beads
comprising a polyamino acid. In yet a further aspect, the deposit
of silica shell on the surface of polystyrene is conducted at room
temperature. In another aspect, the deposit of silica shell on the
surface of polystyrene is conducted under a condition of pH range
from 5.5 to 9.5. In yet another aspect, the deposit of silica shell
on the surface of polystyrene is conducted under a condition of pH
7.4. In another aspect, the deposit of silica shell on the surface
of polystyrene is conducted in phosphate buffer. In a further
aspect, the polystyrene core is removed by heating the core-shell
sphere in air at 400-900.degree. C. for 3-6 hours. In one aspect,
the heating temperature is achieved by employing a temperature ramp
rate of from about 0.1.degree. C./min to about 10.degree. C./min.
The polystyrene core can be removed by washing the core-shell
spheres in organic solvents selected from the group consisting of
toluene, dichloromethane, chloroform, tetrahydrofuran,
dimethylformamide, and any combination thereof. In one aspect, the
polystyrene core is removed by washing the core-shell spheres in
toluene.
[0010] The disclosure also provides a hollow sphere made according
a methods described above. In one aspect, the hollow sphere
comprises a surface amino group or adsorbed polyamines as carriers
of an oligonucleotide or polynucleotide. In another aspect, the
hollow spheres are loaded with a biological agent. The biological
agent can be a polynucleotide, oligonucleotide, small molecule
agent, a peptide or polypeptide and the like. In another aspect,
the hollow spheres can be formulated with a pharmaceutically
acceptable carrier. The hollow sphere can be functionalized to
associate the hollow sphere with a target analyte or cell
[0011] The disclosure also provides methods of nucleic acid
delivery comprising linking an oligonucleotide or polynucleotide to
the hollow sphere of the disclosure and contacting a cell or
subject with the hollow sphere-linked nucleic acid composition
[0012] The disclosure also provides a use of polymer template core
shell or hollow silica nanoparticles with surface amine groups or
adsorbed polyamines as carriers of DNA for gene transfection.
[0013] The disclosure provides an optimized anti-tumor DNA vaccine
using multifunctional nanoparticles. The hollow silica-NPs are
expected to have very low toxicity and improved degradation
profiles compared to solid particles. The methods and compositions
of the disclosure demonstrate that these hollow silica-NPs readily
form complexes with plasmid DNA and can enhance the uptake and
expression of plasmid encoded genes by human dendritic cells
(DCs).
[0014] In addition, the disclosure provides a peptide (Hp-91)
derived from the endogenous molecule HMGB-1, that acts as a potent
stimulus for DC activation and induction of CTL responses in both
mouse and human systems.
[0015] Additional aspects of the invention will be understood from
the description below, the attached drawings and the appended
claims.
DESCRIPTION OF DRAWINGS
[0016] FIG. 1 is a schematic chemical reaction of one method of the
disclosure. Schematic the chemical reaction of one method of the
disclosure (1=silicic acid, 2=polystyrene or latex beads,
3=polyamino acid or polyamine coating to aid deposition of silica
shell, 4=silica shell, 5=hollow silica sphere). For titania spheres
the added polyamino acid or polyamine coating is not needed and
Ti(O-t-Bu)4 is the source titania for the solution reaction. Not to
scale.
[0017] FIG. 2 is a photomicrograph of the core-shell
polystyrene/silica spheres given by the method of the disclosure.
(Left) Scanning electron microscope photomicrograph of core-shell
silica nanoparticles template on 200 nm beads; (the scale bar is
200 nm). (Right) Transmission electron microscopy photo of hollow
silica nanoparticles templated on 100 nm beads and calcined/burned
to remove the polystyrene template; (the scale bar is 100 nm).
[0018] FIG. 3 is a photomicrograph of the hollow silica spheres
given by the method of the disclosure. The silica shell is
templated by 100 nm beads. (SEM instrument used)
[0019] FIG. 4 is a photomicrograph of a hollow silica sphere given
by the method of the present disclosure. The silica shell is
templated by 100 nm beads. (TEM instrument used for image)
[0020] FIG. 5 is a photomicrograph of the hollow titania spheres
prepared by the method of the disclosure. The titania shell shown
is templated by 200 nm beads. (SEM instrument used)
[0021] FIG. 6 is a photograph of DNA adsorbed to hollow silica
spheres. 2 .mu.g or 6 .mu.g plasmid DNA were complexed with
different amounts (0.48-3.8 mg/ml) of either uncharged (top panel)
or charged (bottom panel) silica spheres. Plasmid only, silica
spheres only, as well as the complexes were resolved on a 1%
agarose gel at 100V for 1 h. (Geldoc used for image).
[0022] FIG. 7 is a photograph of DNA adsorbed to hollow silica
spheres: testing DNA-silica sphere complex stability. Aliquots from
each step of the buffer exchange procedure were collected and
resolved on a 1% agarose gel at 100V for 1 h. U=uncharged silica
spheres and C=charged silica sphere-DNA complexes.
[0023] FIG. 8 shows GFP-expression in silica sphere-DNA complex
transfected DCs. Immature human DCs were exposed to different
dilutions of the silica sphere-DNA complexes. 48 h later Gfp
expression was measured by flow cytometry gated on live cells. The
histograms depict the relative fluorescence intensity at the
different dilutions of charged silica sphere-DNA complexes added to
the DCs. B) Percentage of DCs expressing Gfp at 48 h after exposure
to different dilutions of charged silica sphere-DNA complexes or
uncharged silica sphere-DNA complexes. In FIGS. 6-8 uncharged is
defined as 100 nm silica spheres with the polystyrene core removed
by solvent extraction and charged spheres are defined as the 100 nm
silica spheres with the polystyrene core removed by solvent
extraction, but containing surface amino group by treatment with
(MeO).sub.3Si(CH.sub.2).sub.3NH.sub.2.
[0024] FIG. 9 shows a photomicrograph of uptake of Silica
nanoparticles by dendritic cells. Immature human DCs were exposed
to 200 nm FITC-labeled core-shell Silica-NPs. (left) 2 h after
endocytosis, the cells were imaged in bright-field using an
inverted fluorescence microscope (40.times. magnification). (right)
6 h after exposure, the nuclei were stained with Hoechst (blue) and
the cells were imaged using a confocal microscope (60.times.
magnification). The white arrows point to the location in the
nucleus where nanoparticles were observed.
[0025] FIG. 10A, FIG. 10B and FIG. 10C show adsorption of DNA to
hollow silica-NPs. 2 .mu.g or 6 .mu.g plasmid DNA were complexed
with different amounts (0.48-3.8 mg/ml) of hollow silica-NPs. The
same NP concentrations are used in all of the gels. Plasmid only,
nanoparticles only, as well as the complexes were resolved on a 1%
agarose gel at 100V for 1 h. FIG. 10A) Comparison of hollow solvent
extracted unmodified and NH2-modified silica NPs. FIG. 10B)
Comparison of burned hollow silica NPs with different surface
modifications: unmodified, aminemodified, and poly-L-Lysine (pLL)
modified. FIG. 10C) Comparison of DNA adsorption to different size
(120, 80, and 45 nm) unmodified solvent extracted silica-NPs.
DETAILED DESCRIPTION
[0026] As used herein and in the appended claims, the singular
forms "a," "and," and "the" include plural referents unless the
context clearly dictates otherwise. Thus, for example, reference to
"a nanoparticle" includes a plurality of such nanoparticle and
reference to "the cell" includes reference to one or more cells
known to those skilled in the art, and so forth.
[0027] Also, the use of "or" means "and/or" unless stated
otherwise. Similarly, "comprise," "comprises," "comprising"
"include," "includes," and "including" are interchangeable and not
intended to be limiting.
[0028] It is to be further understood that where descriptions of
various embodiments use the term "comprising," those skilled in the
art would understand that in some specific instances, an embodiment
can be alternatively described using language "consisting
essentially of" or "consisting of"
[0029] Unless defined otherwise, all technical and scientific terms
used herein have the same meaning as commonly understood to one of
ordinary skill in the art to which this disclosure belongs.
Although methods and materials similar or equivalent to those
described herein can be used in the practice of the disclosed
methods and compositions, the exemplary methods, devices and
materials are described herein.
[0030] The publications discussed above and throughout the text are
provided solely for their disclosure prior to the filing date of
the present application. Nothing herein is to be construed as an
admission that the inventors are not entitled to antedate such
disclosure by virtue of prior disclosure.
[0031] The disclosure provides hollow nanospheres, compositions
comprising such hollow nanospheres and methods of using such hollow
nanospheres.
[0032] Hollow silica nanospheres are potentially applicable to drug
delivery and imaging. Hollow silica nanospheres have uniform and
stable wall structures with excellent long term stability. Their
size can be controlled by using polymer templates for their
formation with well-defined diameters accessible from emulsion
polymerization. The porosity of the silica shell is convenient for
loading and releasing of drugs or used to contain a heavy element
(e.g. metal nanoparticle) or magnetic oxides for X-ray or magnetic
contrast reagents. The surface of the hollow silica shell is easily
functionalized by grafting biofunctional groups that may combine
with targeting proteins, antibodies, cells, or tissues.
[0033] Since chemotherapeutic agents have a reduced efficacy in
non-proliferating cells, immunotherapy represents a valuable
treatment option because it is able to eliminate tumor cells
independent of their proliferative state. Tumor associate antigens
have been identified for many tumors and those can serve as target
for the immune system. One of the approaches used to induce immune
responses against cancer cells are DNA vaccines. Injection of
plasmids encoding cancer-related antigens or polypeptides can
induce immune responses against the transgene product, offering a
potential method for immunization without requiring production and
purification of complex antigens. Dendritic cells (DCs) are
required to initiate the immune response to the transgene
antigen(s) encoded by such DNA vaccines and cytotoxic T lymphocytes
(CTLs) play a major role in eliminating malignant cells by
specifically recognizing antigenic peptides presented on MHC class
I molecules by dendritic cells (DC). DNA vaccines although showing
some success, are not very efficient and new approaches are needed
to improve efficacy. Hollow silica nanoparticles can serve as a
platform to deliver DNA vaccines.
[0034] Many methods have been employed to fabricate hollow silica
spheres, such as colloidal templating and layer-by-layer (LbL)
self-assembly techniques. Colloidal particles were used to make
core-shell nanospheres of gold, silver, CdS, ZnS and polymer beads;
however, the inorganic templates are difficult to remove from the
core-shell spheres. For those hollow spheres templated with
polymers, their size and uniformity depend on the species and
density of the surface functional groups, which makes size control
difficult. The basis of the LbL technique is the electrostatic
attraction between the charged species deposited. But this method
involves numerous synthetic steps which make large scale production
impractical. The challenge of hollow silica nanoparticle technology
is to find a convenient and inexpensive method to fabricate hollow
silica nanospheres with uniform, stable shell walls, and at the
same time this shell should have acceptable porosity and a narrow
size distribution.
[0035] There is no scalable inexpensive method for making uniform
size distributions of hollow nanoparticles. Current nanoparticles
used for drug delivery and sensing are solid. Hollow nanoparticles
offer the possibility of filling with a payload of drug, imaging
agent, or other material. The outer and inner surfaces could also
be differentially functionalized.
[0036] During the past decade, there has been intense interest
about the fabrication of hollow SiO.sub.2 nanoparticles because of
their applications such as drug delivery, ultrasound imaging,
catalyst, filters, photonic band gap materials. In reported
fabrication protocols, colloidal templating and layer-by-layer
(LbL) self-assembly technique are most usually used. Colloidal
templates used include gold, silver, CdS, ZnS and polymer beads.
Polystyrene (PS) beads are attractive nanoscale templates since
they are inexpensive and their size is easily varied. Furthermore
their surface can be functionalized by chemical and physical
techniques. Finally they are well-suited to make hollow particles
since the polystyrene template can easily be removed by calcination
or dissolution. Calcination can remove the latex cores and give the
hollow SiO.sub.2 nanoparticles. For example, the size and the
uniformity of the nanoparticles depend in-part upon the density of
the surface functional groups which makes the size control
difficult. Caruso et al reported the fabrication of hollow
SiO.sub.2 nanoparticles through the polymer templated electrostatic
LbL self-assembly of SiO.sub.2 colloid-polymer multilayers,
followed by removal of the templated cores. In this study Caruso
applied poly (diallyldimethylammonium chloride) (PDADMAC), a linear
cationic polyelectrolyte to form the composite multilayer with 25
nm SiO.sub.2 colloid. The size of these particles was generally 500
nm and the majority of shells were broken or collapsed when one
SiO.sub.2--PDADMAC layer was applied.
[0037] Poly-L-lysine (PL) is one of the simplest polyamino acids
with a pH-dependent structure and has been applied in many
biomimetic syntheses of ordered silica structure.
[0038] In addition to the methods of nucleic acid delivery
described herein, the disclosure provides a method of synthesis of
hollow silica nanospheres with controllable size and porous, stable
and uniform walls, which are useful for drug delivery and imaging
materials.
[0039] For example, the DNA-nanosphere complexes of the disclosure
take advantage of the physiological function of a type of white
blood cell, called dendritic cell (DC). DCs are important for
initiation of immune responses. DCs do not take up non-complexed
DNA, and the adsorbtion of DNA to different size nanospheres allows
for effective uptake of DNA and gene expression. The methods and
compositions of the disclosure provide for DNA expression in DCs
using nanospheres resulting in minimal cell death and 3-fold more
cells that express the transgene using 6-fold less DNA than current
state of the art methods.
[0040] In one embodiment, the disclosure provides a hollow silica
sphere made from a silicon-containing compound with silicon atoms
derived from, for example, tetraalkoxysilanes, silicic acid, sodium
silicate and the like. Tetraalkoxysilanes used in disclosure
include, for example, tetrapropoxysilane, tetraethoxysilane and
tetramethoxysilane. The disclosure can include other
tetraalkoxysilanes, trialkoxysilanes or dialkoxysilanes. In one
embodiment, the silicon-containing compound is hydrolyzed under
acidic condition before it reacts to form a silica shell.
[0041] The disclosure further provides a method for synthesis of
hollow silica spheres. Commercial polystyrene or latex beads and
their amine or carboxylate functionalized derivatives can be used
in the disclosure as templates. The polymer core template used in
the disclosure can have a narrow size distribution and can be
chosen from about 10 nm to about 1 .mu.m (typically about 20-40,
40-60 or 80-100 nm, but may be larger). A polyamino acid (e.g.,
poly-L-lysine), or any other polyamine, can be used in the
disclosure with the core template mixture. A silicon-containing
compound is added to react under conditions that cause the
deposition of a silica gel shell on the polystyrene beads to form a
uniform silica layer on the template. The polyamino acids can be
washed away after the reaction. The polystyrene core is then
removed by calcinations or solvent extraction. Both methods of core
removal provide a hollow silica sphere with a uniform, porous,
stable silica shell.
[0042] The polystyrene beads and the polystyrene or latex beads
with amine or carboxylate functionalized surfaces, which are used
in disclosure, can be purchased from Polysciences Inc and
Invitrogen Co. The size of templates can be 10 nm, 20 nm, 30 nm, 45
nm, 80 nm, 100 nm, 200 nm, 500 nm, 750 nm or 1000 nm and both
smaller and larger sized templates can be used (e.g., from about 10
nm to 2000 nm). These beads are monodisperse microspheres and are
packaged as 2.0-4.0% solids (w/v) aqueous suspensions. These
polystyrene microspheres can also contain surface primary amine
groups or surface carboxylate groups. The polymer beads may also
contain a fluorescent dye or other chemical or particle. These
sizes typically vary by about 10% from batch to batch of
manufacturer. After coating using the methods of the disclosure the
size increases by 10-15 nm, but solvent washing shrinks them
slightly and those that are calcined shrink more. The larger ones
tend to shrink more. This occurs due to partial dehydration, as the
shell initially forms as a silica gel coating and on removal of
water dehydration to silica of varying degrees of hydration occurs.
After calcining they comprise rigid hollow balls of porous glass
like silica that undergo no further or limited size change.
[0043] The disclosure provides for the use of polyamine or
polyamino acid templates, which gives a high yield of well formed
spheres. The polyamines used in disclosure are homopolymers of
amino acids or aliphatic amines with primary amine groups on the
polymer backbone. Such polyamino acids are poly-L-lysine,
poly-L-arginine, and polyornithine, including solids or their
aqueous solution, typically about a 0.1% poly-L-lysine aqueous
solution. On type of homopolymer of aliphatic amine is
polythyleneimine. The polystyrene beads or latex beads themselves
can template the deposition of a silica shell, but without the
presence of polyamine these core-shell spheres have an irregular
silica shell which collapses during the procedure for removing the
cores. The concentration of polyamino acids used in the disclosure
is kept at low levels to avoid the formation of solid silica
spheres templated by polyamino acids alone, which occurs at higher
polyamino acid concentrations.
[0044] As in the sketch of FIG. 1, the polystyrene or latex beads
are mixed with polyamino acids or polyamine before the hydrolyzed
tetraalkoxysilane solution is added. The dispersion of beads and
0.1% w/v polyamino acid aqueous solution are added to a phosphate
buffer. The ratio of 0.1% w/v polyamino acids and the 2.75% w/v
polystyrene beads is from 1:1 to 10:1 v/v and most preferably 4:1.
The final concentration of the polystyrene beads in the buffer
solution is from 1:1000 to 1:10000 w/v but typically about 1:666
w/v.
[0045] One method of the disclosure is depicted in FIG. 1. As shown
in FIG. 1, tetraalkoxysilane is hydrolyzed under acidic conditions
to form silicic acid (1). Then (1) is added to a mixture of
polystyrene or latex beads (2) and polyamino acid or polyamine (3).
By selecting appropriate reaction conditions such as temperature,
pH, and reaction time the polycondensation of silicic acid occurs
and a silica gel shell (4) is deposited on the polystyrene beads.
The core-shell spheres are collected, washed and calcined at high
temperature to remove the polymer core to give hollow silica
(partially dehydrated silica gel) spheres (5).
[0046] One method of making a nanostructure of the disclosure is
depicted in FIG. 1. Template particle 2 is used in the methods of
the disclosure. The template particles can be, for example, a latex
or polystyrene bead. The template particle 2 comprises a silicic
acid moiety 1. The template particle 2 is then treated to comprise
a polyamino acid or polyamine group 3. The polyamino acid or
polyamine group facilitate silica deposition. A silica shell 4 is
then deposited on the template 2. In one aspect, the template
nanostructure is degraded to provide a hollow nanostructure of the
invention. In other embodiments, the template nanostructure remains
intact. For titania spheres the added polyamino acid or polyamine
coating is not needed and Ti(O-t-Bu).sub.4 is the source titania
for the solution reaction.
[0047] The nanostructures may be used with or without decomposing
the template material. Batch fabrication is straightforward. The
characteristics of the resulting hollow sphere make the
nanostructures useful for application in molecular medicine and in
ultrasensitive Raman, biomolecular, and cellular imaging.
[0048] Various polymers may be used as the template nanostructure
in the generation of a nanostructure of the disclosure. For
example, o-polyacrylamide and poly(vinyl chloride), poly(vinyl
chloride) carboxylated, polystyrene, polypropylene and poly(vinyl
chloride-co-vinyl acetate co-vinyl) alcohols, may be used.
[0049] The ready availability of monosized polystyrene spheres
between 45 and 500 nm provide a mass produced template for the high
yield synthesis of mono-dispersed hollow silica-NPs with porous
shell walls. The polymer spheres readily adsorb a monolayer of
poly-L-lysine and other amino polymers in aqueous solution, which
then serve as a basic catalyst coating for the gelation of silicic
acid (Scheme I).
##STR00001##
[0050] The positively charged poly-L-lysine chains in neutral
buffer solution facilitate the polycondensation reaction of silicic
acid. This rapidly yields a silica shell, which is similar to the
neutral conditions used for polyamino acid templating of biosilica
in organisms, such as diatoms. The silica gel forms around the
poly-L-lysine in a thin (5-10 nm) layer on the outer surface of the
polystyrene spheres. These particles can be isolated and partially
dehydrated by extraction with anhydrous solvents, such as ethanol,
to yield stable core shell particles. The polymer core can be
loaded with fluorescent labels to track the location of the
nanoparticles. Dynamic light scattering measurements confirm that
the particles can be resuspended by mild ultrasonic agitation to
produce aqueous colloidal dispersions with similar polydispersities
as the original polymer beads. The core shell particles can be
heated in air to 450.degree. C., whereupon the polymer core and
poly-L-lysine framework undergo complete oxidation to leave a
hollow porous continguous silica gel nanoshell, which is slightly
smaller than the polymer template. Dehydration of the silica shell
on drying causes a slight shrinkage of the gel layer. The method of
synthesis, SEM, and TEM images for two different sizes of hollow
nanoparticles that have been prepared are shown in FIG. 2. Notice
the high degree of reproducibility of the nanoshells in the bulk
sample.
[0051] FIG. 2 shows a photomicrograph of the core-shell
polystyrene/silica spheres synthesized by the method related to the
disclosure. The core-shell spheres in the photomicrograph are
templated by 100 nm amine functionalized polystyrene beads. After
coating with the silica shell and drying in vacuum, the diameter of
the core-shell spheres is 126.+-.5 nm.
[0052] Fourier Transform Infrared Spectroscopy (FTIR) spectroscopy
was also used to monitor removal of the polystyrene core. The C--H
(Ar) and --CH.sub.2-- of the polystyrene stretching vibrations
occur at 3030-2800 cm.sup.-1. The absorption bands between 1480 and
1400 cm.sup.-1 are from C--H bending vibrations. These features
disappear completely after calcination. When using the dissolution
method to remove the APS core, the FTIR spectrum shows that about
25% of the polystyrene remained. The amount of poly-L-lysine
present in all cases was very low and the N--H stretches could not
be observed before or after removal by calcination or organic
solvents.
[0053] In the disclosure sodium phosphates can be used to make
buffers with different pH. The concentration of the phosphates in
buffer can be about 0.1M. The deposit of silica shell on
polystyrene beads could be given at the pH range of from 5.5 to
9.5, but typically about pH 7.4. Other buffers can be used to
modify the pH during silica shell formation.
[0054] After the polystyrene or latex beads and polyamino acid or
polyamine are mixed in the phosphate buffer, hydrolyzed
tetraalkoxysilane is added to the mixture to deposit silica shell
on the beads. The addition of hydrolyzed tetraalkoxysilane is
completed in one portion. The reaction is conducted on an agitator
(e.g., a vortex agitator with the vortex speed of 3000 rpm, which
provides vigorous rapid mixing). The vortex mixing time can be from
about 2 minutes to 30 minutes, but is typically about 5 minutes.
The core-shell spheres are evident by a cloudiness in solution in
very short time. Prolonging the vortex mixing time did not increase
the diameter of the core-shell spheres, which indicates that the
formation of the silica shell on the polystyrene template occurs
within a few minutes.
[0055] The reaction is typically conducted at room temperature. The
final concentration of hydrolyzed tetraalkoxysilane in the reaction
system is from about 10.sup.-3M to 5.times.10.sup.-3M and typically
about 2.times.10.sup.-3M. A useful concentration of hydrolyzed
tetraalkoxysilane provides a uniform and stable silica shell around
the templates with narrow size distribution range, and in high
yield based on the template. Higher concentrations of hydrolyzed
tetraalkoxysilane do not give a thicker silica shell but yield
solid silica spheres as byproducts.
[0056] The core-shell spheres can be isolated from solution by
centrifugation. The white precipitate can be washed by being
dispersed in deionized water and centrifuged. These procedures are
followed by washing the spheres with ethanol. These washing
procedures in the disclosure are to remove excess reactant and
phosphate buffer and are optional. After collection of the pure
core-shell spheres by centrifugation, the polystyrene core can be
removed, although it may not be desirable depending upon further
processing or intended use.
[0057] Two methods can be used to remove the polystyrene core are
calcination and dissolution, preferably the method of calcination.
To remove the core by dissolution, the core-shell precipitate is
suspended in toluene and the mixture is stirred 1 hour at room
temperature and then collected by centrifugation. The washing
procedure is repeated three more times and then the hollow spheres
are washed twice with ethanol. The first solvent used in this step
may be extended to dichloromethane, chloroform, ethylene diamine,
tetrahydrofuran, or dimethylformamide. The final product of the
disclosure is obtained by drying at 60.degree. C. under vacuum for
48 hours. To remove the polystyrene cores by calcinations, the
core-shell spheres are dried at 60.degree. C. under vacuum for 48
hours, and then heated in air at 400-900.degree. C. for 3-6 hours,
more preferably heating at 450.degree. C. for 4 hours. Temperature
ramp and decline rates are from 0.1.degree. C./min to 10.degree.
C./min, most preferably 5.degree. C./min.
[0058] Hollow NP allow for independent surface conjugation of the
exterior and interior surfaces. The hollow silica-NPs have uniform
and stable wall structures with excellent stability for long term
storage. Their size can be controlled by using polymer templates
for their formation with well-defined diameters accessible from
emulsion polymerization. The porosity of the silica shell is also
convenient for loading of small molecules, such as drugs or short
peptides in the core. The surface of the hollow silica-NPs is
easily functionalized by grafting functional groups (e.g. amino
groups as in Scheme II) that may combine with targeting proteins,
antibodies, cells, or tissues. Hollow silica-NPs can also be made
to contain other smaller nanoparticles, including Q-dots to monitor
their position via fluorescence. Polystyrene beads were coated with
poly-L-Lysine to template 100 nm core-shell silica-NPs; the surface
was functionalized with (MeO).sub.3Si(CH.sub.2).sub.3NH.sub.2
either before or after the polymer core was removed by calcination
or organic solvents (FIG. 1). For the calcinated particles, the
surface coating is introduced at the end. The hollow Silica-NPs
were functionalized with 3-aminopropyl (trimethoxy) silane as in
Scheme II to add the additional amine groups. These are referred to
as amine-modified silica-NPs. For example, 1 mg of calcinated
hollow silica spheres, prepared from the 100 nm templates, was
suspended in 2 mL of 1% 3-aminopropyl (trimethoxy) silane acetone
solution. The mixture was stirred slowly for 2 hours with a
magnetic stirrer followed by collecting the particles by
centrifugation. The collected particles were washed with ethanol
and dried in vacuum for 24 hours at room temperature. On a 100 nm
sphere about 2400 or more surface attached amino groups can be
obtained. Both small molecules and peptides containing a free
carboxylic acid moiety can be coupled by the coupling reaction to
the surface amines with EDAC
(1-Ethyl-3-(3-dimethylaminopropyl)carbodiimide, hydrochloride) to
form an amide bond.
##STR00002##
[0059] FIG. 3 shows a photomicrograph of the hollow silica spheres
given by the disclosure. The size of the hollow silica spheres is
205.+-.7 nm. FIG. 4 is a photomicrograph of a hollow silica sphere.
As FIG. 1 shows, the tetraalkoxysilane is hydrolyzed in aqueous
acid solution. The acid used to hydrolyze the tetraalkoxysilanes is
0.01 M hydrochloric acid aqueous solution. In the disclosure the
acids may be extended to sulfuric acid and nitric acid and by
inference any other acid with a noninterfering anion. The
tetraalkoxysilane could be tetrapropoxysilane, tetraethoxysilane or
tetramethoxysilane, most preferably tetramethoxysilane. In the
disclosure the precursor of silica shell may be extended to
trialkoxysilanes or diaalkoxysilanes, and by inference any source
of silicic acid could be used. The final concentration of
tetraalkoxysilane in the acid is about 0.1-10M and but is typically
about 1 M. The time of hydrolysis reaction is from about 5 minutes
to 60 minutes, but typically about 15 minutes. The hydrolysis
reaction is conducted at room temperature.
[0060] Table 1 shows the variation of the size of hollow silica
spheres to the size of templates and the methods of removing the
polystyrene cores. After removing templates the diameter of the
silica shell shrinks, depending on conditions for core removal and
template size. The hollow silica spheres made from large templates
shrink more than those made from small templates. The hollow silica
spheres obtained by calcination shrink more than those prepared by
dissolution. The size distribution ranges of all of the hollow
silica spheres made by the disclosure are less than 10%. Since the
initially formed wall consists of silica gel, shrinkage of the wall
is expected when the gel dries and partial dehydration occurs
during calcinations or extractions with anhydrous solvents.
[0061] A final product of the disclosure is a white powder
consisting of nanospheres that is easily suspended in deionized
water, neutral phosphate buffer, methanol, ethanol, toluene or
dichloromethane. Sonication for 15-30 minutes aids resuspension of
the nanoparticles.
[0062] In the disclosure the hollow silica spheres obtained are
functionalized with 3-aminopropyl(trimethoxy)silane. To do the
functionalization the hollow silica spheres, after calcinations,
are dipped in 1% 3-aminopropyl(trimethoxy)silane acetone solution.
The ratio of hollow silica spheres and the
3-aminopropyl(trimethoxy)silane is from 1:10 to 1:100, preferably
1:20. The reaction is induced by a magnetic stirrer at room
temperature and the reaction time is from about 30 minutes to 4
hours, typically about 2 hours. The amine functionalized hollow
spheres are washed by deionized water and ethanol, followed by
drying under vacuum at room temperature. The surface
functionalization reaction can also be induced before removing the
template with organic solvents. By this method the functionalized
reaction occurs predominantly on the outside surface of the
core-shell spheres. After removing the template the inside surface
of the silica shell can be functionalized with different chemistry.
Materials, which could react or interact with the surface of the
hollow silica spheres are used for functionalization and, include
trialkoxy- or triaryloxysilanes, dialkoxy- or diaryloxysilanes,
alkoxy- or aryloxysilanes, derivatives thereof (i.e., oligametic or
polymeric). For example, 3-mercaptopropyl(triethoxy)silane may
react with the surface of hollow silica spheres and functionalize
the surface with thiol groups. Amine groups or thiol groups on the
surface of hollow silica spheres allow coupling with biomaterials,
such as antibodies, proteins, enzymes, or DNA. After loading with
drugs or heavy gas these kinds functionalized silica spheres may
have diverse applications for targeted drug delivery or targeted
contrast-enhanced imaging. In addition, the adsorptive properties
of silica gel allow reversible adsorption of materials, as expected
from the properties of silica gel like surfaces. The hollow nature
of these nanoparticles also imparts them with a high surface area,
as each particle contains an inner and outer surface.
[0063] The polystyrene beads or latex beads with amine
functionalized surface could also be used as template to prepare
hollow TiO.sub.2 spheres using a similar procedure. The precursor
of the TiO.sub.2 shell is titanium t-butoxide. The synthesis of
TiO.sub.2 spheres is conducted in ethanol without the addition of
polyamine. The ratio of template and titanium t-butoxide, the
temperature and the time of reaction, and the method of removing
the template are same as with the synthesis of silica spheres.
Monodispersed hollow spheres with a uniform and porous TiO.sub.2
wall are obtained with yield of 85-95%. Other metal alkoxides,
which undergo sol-gel type reactivity are expected to react
similarly and form hollow shells either with our without added
polyamine template.
[0064] Some advantages of the disclosure are: using commercial
polystyrene beads and their amine of carboxylate functionalized
derivatives as templates to prepare silica nanoshells of uniform
size with porous walls in high yield. These hollow nanoparticles
could be prepared on a large scale and their size could be
controlled from 40 nm to 1 um. The ability to surface functionalize
the silica shell will allow diverse applications of the hollow
silica nanospheres. Dissolution of the polymer core under mild
conditions should allow differential functionalization of the
hollow shell inner and outer surfaces.
[0065] The disclosure also provides a method to functionalize the
surface of hollow silica spheres. For example, a
3-aminopropyl(trimethoxy)silane is used to react with the SiO.sub.2
shell to provide an amine functionalized surface, which can then be
crosslinked to proteins or used to adsorb DNA for diverse
biological applications. This functionalization can be induced
before or after removing of the template by organic solvents or
after removing the template by calcination.
[0066] In yet another aspect, a metal particle or metal containing
material can be incorporated into the hollow silica nanosphere. In
this aspect, an aqueous colloidal suspension of a metal oxide
nanoparticle precursor is added to a polyamino polystyrene
composition, prior to contacting with a silicon containing
compound.
[0067] The disclosure further provides a method for adsorbing DNA
to hollow silica nanospheres. These complexes can be used to
deliver oligonucleotide or polynucleotides (e.g., DNA or RNA or
analogs thereof) into mammalian cells in a tissue culture dish for
transgene expression as well as for vaccine purposes in vivo. For
example, the DNA can encodes genes for cancer vaccines or viral or
bacterial vaccines for prevention and therapy.
[0068] The disclosure provides nanostructures that are
biocompatible and can be "loaded" with biological agents or other
materials (e.g., drugs, metallic compositions, magnetic
compositions and the like).
[0069] Although the specific examples provided herein demonstrate
particular aspects of the hollow nanostructure of the disclosure,
one of skill in the art will recognize that the size, shape, and
layer thickness can all be individually controlled. Owing to its
hollowness, the inner and outer surfaces can be modified with
different materials for a wide variety of characteristics and
functions.
[0070] The nanostructures of the disclosure are biocompatible, and
thus can be biofunctionalized and applied in real-time biomolecular
imaging as well as drug delivery. The term "functionalized" is
meant to include functional groups attached to the surface of a
nanostructure of the disclosure.
[0071] The nanostructures of the disclosure can optionally be
functionalized by imprinting functional groups, such as antibodies,
proteins, nucleic acids, and the like. Such nanostructures are
particularly useful for molecular diagnostics and drug delivery.
For example, to prolong or target analyte interaction with the
hollow nanoparticle surface, a binding agent/targeting domain can
be used to promote interaction of a nanostructure with a desired
target.
[0072] In other embodiments, nanostructures of the disclosure are
coated to inhibit the accumulation of biological material (e.g.,
proteinaceous agents) on the nanostructure's surface. In some
embodiments, polyethyleneglycol (PEG) is immobilized on
nanostructure surfaces to prevent nonspecific interactions.
[0073] Attached functional groups can comprise components for
specifically, but reversibly or irreversibly, interacting with the
specific analyte (e.g., can be labeled for site/molecule directed
interactions). For example, a surface bound functional group (e.g.,
a targeting ligand) can be attached to a nanostructure of the
disclosure. For example, a chemical molecule can be immobilized on
the surfaces of a nanostructure of the disclosure.
[0074] A targeting ligand can include a receptor bound to the
surface of a nanostructure of the disclosure that interacts
reversibly or irreversibly with a specific analyte. Examples of
functional groups (e.g., targeting ligands) include
antigen-antibody pairs, receptor-ligand pairs, and carbohydrates
and their binding partners. The binding ligand may be nucleic acid,
when nucleic acid binding proteins are the targets. As will be
appreciated by those in the art, the composition of the binding
ligand will depend on the composition of the target analyte.
Binding ligands to a wide variety of analytes are known or can be
readily identified using known techniques.
[0075] For example, when the analyte is a single-stranded nucleic
acid, the binding/targeting ligand is generally a substantially
complementary nucleic acid. Similarly the analyte may be a nucleic
acid binding protein and the capture binding ligand is either a
single-stranded or double-stranded nucleic acid; alternatively, the
binding ligand may be a nucleic acid binding protein when the
analyte is a single or double-stranded nucleic acid. When the
analyte is a protein, the binding ligands include proteins or small
molecules. For example, when the analyte is an enzyme, suitable
binding ligands include substrates, inhibitors, and other proteins
that bind the enzyme, i.e. components of a multi-enzyme (or
protein) complex. As will be appreciated by those in the art, any
two molecules that will associate, may be used, either as the
analyte or the functional group (e.g., targeting/binding ligand).
Suitable analyte/binding ligand pairs include, but are not limited
to, antibodies/antigens, receptors/ligand, proteins/nucleic acids;
nucleic acids/nucleic acids, enzymes/substrates and/or inhibitors,
carbohydrates (including glycoproteins and glycolipids)/lectins,
carbohydrates and other binding partners, proteins/proteins; and
protein/small molecules. In one embodiment, the binding ligands are
portions (e.g., the extracellular portions) of cell surface
receptors.
[0076] The disclosure provides nanostructures that have use in the
detection of analytes in the environment, including explosive and
biological agents as well as in vivo. Accordingly, the invention is
useful in Homeland Security and the military for detection of
analytes as well as for medical diagnostics. In one embodiment, the
disclosure provides kits for monitoring military personnel in a war
situation where they may be exposed to toxins. The nanostructures
are administered or contacted with the subject prior to potential
exposure. The subjects can then be monitored at set intervals using
a detection device.
[0077] Commercial applications include environmental toxicology,
materials quality control, food and agricultural products
monitoring, anesthetic detection, automobile oil or radiator fluid
monitoring, hazardous spill identification, medical diagnostics,
detection and classification of bacteria and microorganisms both in
vitro and in vivo for biomedical uses and medical diagnostic uses,
infectious disease detection, body fluids analysis, drug discovery,
telesurgery, illegal substance detection and identification, and
the like.
[0078] Applications for the nucleic acid constructs provided herein
include selective treatment of cancer, viral infection, genetic
diseases, nucleic acid delivery for research and the like.
[0079] Provided herein are hollow nanospheres than can be used for
the delivery of biological agents to a cell in vitro or in vivo.
The biological agent can be a nucleic acid (e.g., a polynucleotide,
oligonucleotide, peptide or polypeptide). In one aspect, a nucleic
acid of interest is conjugated or operably linked to a hollow
nanosphere of the disclosure.
[0080] An isolated nucleic acid construct refers to an
oligonucleotide or polynucleotide associated with a hollow
nanopshere of the disclosure. For example, a nucleic acid construct
includes, but is not limited to, an oligonucleotide or
polynucleotide associated with hollow silica nanopshere as
described herein either directly or via a functional linker. An
oligonucleotide or polynucleotide in the nucleic acid constructs of
the disclosure include fusion polypeptides or peptides, chemical
moieties that reduce the net anionic charge of an oligonucleotide
or polynucleotide and combinations thereof.
[0081] The term polynucleotide(s) and oligonucleotide(s) generally
refers to any polyribonucleotide or polydeoxyribonucleotide, which
may be unmodified RNA or DNA or modified RNA or DNA. Thus, for
instance, an oligonucleotide as used herein refers to, among
others, single- and double-stranded DNA, DNA that is a mixture of
single- and double-stranded regions, single- and double-stranded
RNA, and RNA that is mixture of single- and double-stranded
regions, hybrid molecules comprising DNA and RNA that may be
single-stranded or, more typically, double-stranded or a mixture of
single- and double-stranded regions. Thus, a oligonucleotide can
comprise an siRNA, an antisense molecule, a ribozyme and the like.
For example, in one aspect of the disclosure the siRNA can comprise
(fomivirsen) an antisense drug to treat a condition called
cytomegalovirus (CMV) retinitis. Other suitable siRNA molecules
will be apparent to those of skill in the art. Furthermore, it will
be recognized that expression vectors or gene delivery
constructions comprising DNA, RNA, a combination of DNA and RNA,
and vectors or constructs comprising nucleic acid analogs can be
adsorbed to the hollow silica nanospheres of the disclosure. The
vector or construct can comprise any of a large number of
therapeutic, diagnostic or research genetic sequences encoding
enzymes, inhibitors, antisense, siRNA, ribozymes, and therapeutic
proteins known in the art, such molecules are known or easily
identified in the art (e.g., GFP, growth factors, enzymes, soluble
domains of receptor ligands and the like).
[0082] In addition, a polynucleotide or oligonucleotides also
includes triple-stranded regions comprising RNA or DNA or both RNA
and DNA. The strands in such regions may be from the same molecule
or from different molecules. The regions may include all of one or
more of the molecules, but more typically involve only a region of
some of the molecules.
[0083] In some aspects a polynucleotide or oligonucleotide includes
DNAs or RNAs as described above that contain one or more modified
bases. Thus, DNAs or RNAs with backbones comprising unusual bases,
such as inosine, or modified bases, such as tritylated bases, are
polynucleotides or oligonucleotides as the term is used herein.
[0084] As used herein, a nucleic acid domain, used interchangeably
with oligonucleotide or polynucleotide domain, can be any
oligonucleotide or polynucleotide (e.g., a ribozyme, antisense
molecule, polynucleotide, oligonucleotide and the like).
Oligonucleotides or polynucleotides generally contain
phosphodiester bonds, although in some cases, nucleic acid analogs
are included that may have alternate backbones, comprising, e.g.,
phosphoramidate, phosphorothioate, phosphorodithioate, or
O-methylphophoroamidite linkages (see Eckstein, Oligonucleotides
and Analogues: A Practical Approach, Oxford University Press); and
peptide nucleic acid backbones and linkages. Other analog nucleic
acids include those with positive backbones; non-ionic backbones,
and non-ribose backbones, including those described in U.S. Pat.
Nos. 5,235,033 and 5,034,506, and Chapters 6 and 7, ASC Symposium
Series 580, Carbohydrate Modifications in Antisense Research,
Sanghui & Cook, eds. Nucleic acids containing one or more
carbocyclic sugars are also included within one definition of
nucleic acids. Modifications of the ribose-phosphate backbone may
be done for a variety of reasons, e.g. to increase the stability
and half-life of such molecules in physiological environments.
Mixtures of naturally occurring nucleic acids and analogs are
encompassed by the term oligonucleotide and polynucleotide;
alternatively, mixtures of different nucleic acid analogs, and
mixtures of naturally occurring nucleic acids and analogs can be
made. Furthermore, hybrids of RNN, RNB, DNA, and RNA can be used.
dsDNA, ssDNA, dsRNA, siRNA are encompassed by the term
oligonucleotide and polynucleotide.
[0085] A polynucleotide refers to a polymeric compound made up of
any number of covalently bonded nucleotide monomers, including
nucleic acid molecules such as DNA and RNA molecules, including
single- double- and triple-stranded such molecules, and is
expressly intended to embrace that group of polynucleotides
commonly referred to as "oligonucleotides", which are typically
distinguished as having a relatively small number (no more than
about 30, e.g., about 5-10, 10-20 or 20-30) of nucleotide
constituents.
[0086] As used herein, the term "siRNA" is an abbreviation for
"short interfering RNA", also sometimes known as "small interfering
RNA" or "silencing RNA", and refers to a class of about 19-25
nucleotide-long double-stranded ribonucleic acid molecules that in
eukaryotes are involved in the RNA interference (RNAi) pathway that
results in post-transcriptional, sequence-specific gene
silencing.
[0087] The term "dsRNA" is an abbreviation for "double-stranded
RNA" and as used herein refers to a ribonucleic acid molecule
having two complementary RNA strands and which stands distinct from
siRNA in being at least about 26 nucleotides in length, and more
typically is at least about 50 to about 100 nucleotides in
length.
[0088] As described above, the nucleic acid may be DNA, both
genomic and cDNA, RNA or a hybrid, where the nucleic acid may
contain combinations of deoxyribo- and ribo-nucleotides, and
combinations of bases, including uracil, adenine, thymine,
cytosine, guanine, inosine, xanthine hypoxanthine, isocytosine,
isoguanine, etc. As used herein, the term "nucleoside" includes
nucleotides and nucleoside and nucleotide analogs, and modified
nucleosides such as amino modified nucleosides. In addition,
"nucleoside" includes non-naturally occurring analog structures.
Thus, e.g. the individual units of a peptide nucleic acid, each
containing a base, are referred to herein as a nucleoside.
[0089] The nucleic acid domain of a nucleic acid construct
described herein is not limited by any particular sequence. Any
number of oligonucleotide or polynucleotides useful for
diagnostics, therapeutics and research can be used in the methods
and compositions of the disclosure. Various sources of
oligonucleotides and polynucleotides are available to one of skill
in the art. For example, fragments of a genome may be isolated and
the isolated polynucleotides modified in accordance with the
disclosure to reduce the overall net anionic charge using
phosphodiester and/or phosphothioate protecting groups or may be
used as a source for extension of the oligonucleotide or
polynucleotide using, for example, nucleic acid synthesis
techniques known in the art.
[0090] Delivery of a polynucleotides can be achieved by introducing
the polynucleotide into a cell using a hollow nanosphere of the
disclosure. For example, a construct comprising such a
polynucleotide can be delivered into a cell using a colloidal
dispersion of hollow nanospheres. Alternatively, a polynucleotide
construct can be incorporated (i.e., cloned) into an appropriate
vector which is then linked to the nanosphere. For purposes of
expression, the polynucleotide encoding a fusion polypeptide may be
inserted into a recombinant expression vector. The expression
vector typically contains an origin of replication, a promoter, as
well as specific genes that allow phenotypic selection of the
transformed cells. Vectors suitable for such use include, but are
not limited to, the T7-based expression vector for expression in
bacteria (Rosenberg et al., Gene, 56:125, 1987), the pMSXND
expression vector for expression in mammalian cells (Lee and
Nathans, J. Biol. Chem., 263:3521, 1988), baculovirus-derived
vectors for expression in insect cells, cauliflower mosaic virus,
CaMV, and tobacco mosaic virus, TMV, for expression in plants.
[0091] Depending on the vector utilized, any of a number of
suitable transcription and translation elements (regulatory
sequences), including constitutive and inducible promoters,
transcription enhancer elements, transcription terminators, and the
like may be used in the expression vector (see, e.g., Bitter et
al., Methods in Enzymology, 153:516-544, 1987). These elements are
well known to one of skill in the art.
[0092] The term "operably linked" and "operably associated" are
used interchangeably herein to broadly refer to a chemical or
physical coupling of two otherwise distinct domains that each have
independent biological function. For example, operably linked
refers to the functional linkage between a regulatory sequence and
the polynucleotide regulated by the regulatory sequence. In another
aspect, operably linked refers to the association of a nucleic acid
domain and a transduction domain such that each domain retains its
independent biological activity under appropriate conditions.
Operably linked further refers to the link between encoded domains
of the fusion polypeptides such that each domain is linked in-frame
to give rise to the desired polypeptide sequence.
[0093] Nanoparticles can serve as a delivery platform that allows
for "attachment" of DC-stimuli and antigen on the same particles,
which can then be used for induction of immune responses.
Silica-NPs appear to have the lowest toxicity compared to other
nanomaterials tested.
[0094] The nanostructures of the disclosure can be used in vivo and
in vitro to detect, deliver, identify, and/or characterize analytes
of interest. The nanostructures can be used to detect analytes in
environmental samples as well as samples derived from living
organisms. As used herein, the term "sample" is used in its
broadest sense. For example, a sample can comprise a specimen or
culture obtained from any source, as well as biological and
environmental samples. Biological samples may be obtained from
animals (including humans) and encompass fluids, solids, tissues,
and gases. Biological samples include blood products, such as
plasma, serum and the like. Environmental samples include
environmental material such as surface matter, soil, water,
crystals and industrial samples. The nanostructures can be used,
for example, in bodily fluids in vivo or in vitro. Such bodily
fluids include, but are not limited to, blood, serum, lymph,
cerebral spinal fluid, aqueous humor, interstitial fluid, and
urine.
[0095] Introduction of plasmid DNA into cells for gene expression
is being widely used in biology. Primary cells like dendritic cells
are very difficult to transfect using methods like lipofection that
work very well for cell lines. Electroporation using a specialized
machine and reagents has been commercialized (Amaxa biosystems) and
it is currently, next to viral vectors, the best method on the
market for introduction of plasmid DNA into dendritic cells. This
application uses electric force to introduce DNA into DCs; however,
this method causes a high number of cell death. And gene expression
peaks at 20 h, and at 48 h nearly 30% of the cells are dead and
gene expression is reduced to 10% of the cells.
[0096] Since immature DCs readily take up particles, the methods
and compositions of the disclosure have taken advantage of DCs
natural function and utilized nanoparticles coated with DNA as a
"Trojan horse" to deliver nucleic acids into DCs. In vivo, DCs need
to encounter both the antigen and a DC stimulus for optimal
induction of antitumor Cytotoxic T lymphocytes (CTL) responses. DCs
that encounter antigen without stimulus can induce immune
tolerance, since DCs effectively take up particles. The disclosure
generates multi-functional silica-NPs that carry antigen-encoding
nucleic acids and the DC stimulus to ensure the generation of
strong anti-tumor immune responses. Coupling of nucleic acids and
an immunostimulatory agent or peptide (e.g., Hp-91) on silica-NPs
improves the efficacy of these multifunctional nanoparticles. Such
compositions and methods are demonstrated in the non-limiting
examples below which demonstrate in vitro assays for DC uptake,
activation, and CTL induction and in vivo using a mouse melanoma
model.
[0097] To adsorb a oligo- or poly-nucleotide to hollow SiO.sub.2
spheres, the spheres are resuspended in and appropriate media. In
one aspect, the sphere are resuspended in PBS and sonicated for 15
min to several hours at a setting sufficient enough to resuspend
the spheres. The resuspended spheres are then diluted and mixed
with the desired nucleic acid molecules. For example, different
amounts of SiO.sub.2 spheres were diluted in 700 mM NaCl and 100
.quadrature.l of the dilution was mixed at 10 .quadrature.l per
minute with 100 .quadrature.l of a plasmid dilution under constant
vortexing. Adsorbed nucleic acids can be identified or purified by
filtration or separation. For example, adsorbed nucleic acids was
resolved on an agarose gel after formation of the complexes (FIG.
6). Adsorption of the nucleic acids to the SiO.sub.2 spheres
prevents the DNA from running into the gel and instead it stays in
the wells with the SiO.sub.2 spheres, whereas free unbound plasmid
will run as two bands. Uncharged (defined as 100 nm silica spheres
with the polystyrene core removed by solvent extraction) and
charged (defined as the 100 nm silica spheres with the polystyrene
core removed by solvent extraction, but containing surface amino
group by treatment with (MeO).sub.3Si(CH.sub.2).sub.3NH.sub.2)
SiO.sub.2 spheres were compared. Uncharged SiO.sub.2 spheres were
more effective at adsorbing plasmid DNA. For example, at 0.95 mg/ml
the uncharged SiO.sub.2 spheres adsorbed all of the 2 .mu.g DNA,
whereas twice the amount of charged SiO.sub.2 spheres was required
to adsorb the same amount of DNA.
[0098] To evaluate uptake of SiO.sub.2 sphere-DNA complexes by
primary human dendritic cells (DCs), the SiO.sub.2 spheres-DNA
complexes were sonicated briefly for 15 min at high, spun down at
6000 rpm for 10 minutes, and the pellet was resuspended in culture
media. To test whether the plasmid would disassociate from the
SiO.sub.2 spheres, aliquots were taken before sonication, post
sonication, from the supernatant after the spin, and from the
resuspended pellet (FIG. 7). At all stages the plasmid DNA was
retained in the wells, indicating that neither the sonication nor
the spinning caused the plasmid DNA to disassociate from the
SiO.sub.2 spheres. The same was true for charged and uncharged
SiO.sub.2 spheres.
[0099] Since the plasmid DNA --SiO.sub.2 sphere complexes and was
maintained during exchange of high salt to culture media,
examination of whether immature human DCs would take up the
complexes and express the transgene was analyzed. A plasmid that
encodes for gfp was used, because it allows for easy monitoring of
GFP expression by flow cytometry. 10.sup.5 immature DCs were
exposed to 25 .quadrature.l diluted SiO.sub.2 sphere-DNA complexes
for 2 h and subsequently 1 ml of fresh medium was added to the
cells. DCs were collected 48 h after exposure to the complexes. At
1:10 dilution of the charged SiO.sub.2 sphere-DNA complex (0.075 ug
plasmid DNA per 10.sup.5 cells), a strong shift in mean
fluorescence intensity was observed and 45% of the DCs expressed
GFP (FIG. 8). The uncharged SiO.sub.2 sphere-DNA complexes at the
same dilution showed approximately 2-fold lower percentage of
Gfp-positive DCs, which correlated with the fact that .about.2-fold
less plasmid was adsorbed to the same number of particles charged
SiO.sub.2 spheres (see FIG. 6). Using the "state of the art"
transfection method for DCs, the Amaxa system, which is
electroporation with a specialized machine, only 10-15% of the DCs
expressed GFP at 48 h when 0.5 .quadrature.g plasmid DNA were used
per 10.sup.5 cells, which is 6.6-fold more DNA and the percentage
of cells expressing GFP is 3-fold lower. Thus the SiO.sub.2 spheres
provide a very powerful tool to introduce a transgene into DCs.
[0100] A nanostructure of the disclosure can be formulated with a
pharmaceutically acceptable carrier, although the nanostructure may
be administered alone, as a pharmaceutical composition.
[0101] A pharmaceutical composition according to the disclosure can
be prepared to include a nanostructure of the disclosure, into a
form suitable for administration to a subject using carriers,
excipients, and additives or auxiliaries. Frequently used carriers
or auxiliaries include magnesium carbonate, titanium dioxide,
lactose, mannitol and other sugars, talc, milk protein, gelatin,
starch, vitamins, cellulose and its derivatives, animal and
vegetable oils, polyethylene glycols and solvents, such as sterile
water, alcohols, glycerol, and polyhydric alcohols. Intravenous
vehicles include fluid and nutrient replenishers. Preservatives
include antimicrobial, anti-oxidants, chelating agents, and inert
gases. Other pharmaceutically acceptable carriers include aqueous
solutions, non-toxic excipients, including salts, preservatives,
buffers and the like, as described, for instance, in Remington's
Pharmaceutical Sciences, 15th ed., Easton: Mack Publishing Co.,
1405-1412, 1461-1487 (1975), and The National Formulary XIV., 14th
ed., Washington: American Pharmaceutical Association (1975), the
contents of which are hereby incorporated by reference. The pH and
exact concentration of the various components of the pharmaceutical
composition are adjusted according to routine skills in the art.
See Goodman and Gilman's, The Pharmacological Basis for
Therapeutics (7th ed.).
[0102] The pharmaceutical compositions according to the disclosure
may be administered locally or systemically. By "effective dose" is
meant the quantity of a nanostructure according to the disclosure
to sufficiently provide measurable SERS signals. Amounts effective
for this use will, of course, depend on the tissue and tissue
depth, route of delivery and the like.
[0103] Typically, dosages used in vitro may provide useful guidance
in the amounts useful for administration of the pharmaceutical
composition, and animal models may be used to determine effective
dosages for specific in vivo techniques. Various considerations are
described, e.g., in Langer, Science, 249: 1527, (1990); Gilman et
al. (eds.) (1990), each of which is herein incorporated by
reference.
[0104] As used herein, "administering an effective amount" is
intended to include methods of giving or applying a pharmaceutical
composition of the disclosure to a subject that allow the
composition to perform its intended function.
[0105] The pharmaceutical composition can be administered in a
convenient manner, such as by injection (e.g., subcutaneous,
intravenous, and the like), oral administration, inhalation,
transdermal application, or rectal administration. Depending on the
route of administration, the pharmaceutical composition can be
coated with a material to protect the pharmaceutical composition
from the action of enzymes, acids, and other natural conditions
that may inactivate the pharmaceutical composition. The
pharmaceutical composition can also be administered parenterally or
intraperitoneally. Dispersions can also be prepared in glycerol,
liquid polyethylene glycols, and mixtures thereof, and in oils.
Under ordinary conditions of storage and use, these preparations
may contain a preservative to prevent the growth of
microorganisms.
[0106] Pharmaceutical compositions suitable for injectable use
include sterile aqueous solutions (where water soluble) or
dispersions and sterile powders for the extemporaneous preparation
of sterile injectable solutions or dispersions. The composition
will typically be sterile and fluid to the extent that easy
syringability exists. Typically the composition will be stable
under the conditions of manufacture and storage and preserved
against the contaminating action of microorganisms, such as
bacteria and fungi. The carrier can be a solvent or dispersion
medium containing, for example, water, ethanol, polyol (for
example, glycerol, propylene glycol, and liquid polyethylene
glycol, and the like), suitable mixtures thereof, and vegetable
oils. The proper fluidity can be maintained, for example, by the
use of a coating, such as lecithin, by the maintenance of the
required particle size, in the case of dispersion, and by the use
of surfactants. Prevention of the action of microorganisms can be
achieved by various antibacterial and antifungal agents, for
example, parabens, chlorobutanol, phenol, ascorbic acid,
thimerosal, and the like. In many cases, isotonic agents, for
example, sugars, polyalcohols, such as mannitol, sorbitol, or
sodium chloride are used in the composition. Prolonged absorption
of the injectable compositions can be brought about by including in
the composition an agent that delays absorption, for example,
aluminum monostearate and gelatin.
[0107] Sterile injectable solutions can be prepared by
incorporating the pharmaceutical composition in the required amount
in an appropriate solvent with one or a combination of ingredients
enumerated above, as required, followed by filtered sterilization.
Generally, dispersions are prepared by incorporating the
pharmaceutical composition into a sterile vehicle that contains a
basic dispersion medium and the required other ingredients from
those enumerated above.
[0108] The pharmaceutical composition can be orally administered,
for example, with an inert diluent or an assimilable edible
carrier. The pharmaceutical composition and other ingredients can
also be enclosed in a hard or soft-shell gelatin capsule,
compressed into tablets, or incorporated directly into the
subject's diet. For oral administration, the pharmaceutical
composition can be incorporated with excipients and used in the
form of ingestible tablets, buccal tablets, troches, capsules,
elixirs, suspensions, syrups, wafers, and the like. Such
compositions and preparations should contain at least 1% by weight
of active compound. The percentage of the compositions and
preparations can, of course, be varied and can conveniently be
between about 5% to about 80% of the weight of the unit.
[0109] The tablets, troches, pills, capsules, and the like can also
contain the following: a binder, such as gum gragacanth, acacia,
corn starch, or gelatin; excipients such as dicalcium phosphate; a
disintegrating agent, such as corn starch, potato starch, alginic
acid, and the like; a lubricant, such as magnesium stearate; and a
sweetening agent, such as sucrose, lactose or saccharin, or a
flavoring agent such as peppermint, oil of wintergreen, or cherry
flavoring. When the dosage unit form is a capsule, it can contain,
in addition to materials of the above type, a liquid carrier.
Various other materials can be present as coatings or to otherwise
modify the physical form of the dosage unit.
[0110] For instance, tablets, pills, or capsules can be coated with
shellac, sugar, or both. A syrup or elixir can contain the agent,
sucrose as a sweetening agent, methyl and propylparabens as
preservatives, a dye, and flavoring, such as cherry or orange
flavor. Of course, any material used in preparing any dosage unit
form should be pharmaceutically pure and substantially non-toxic in
the amounts employed. In addition, the pharmaceutical composition
can be incorporated into sustained-release preparations and
formulations.
[0111] Thus, a "pharmaceutically acceptable carrier" is intended to
include solvents, dispersion media, coatings, antibacterial and
antifungal agents, isotonic and absorption delaying agents, and the
like. The use of such media and agents for pharmaceutically active
substances is well known in the art. Supplementary active compounds
can also be incorporated into the compositions.
[0112] The working examples provided below are to illustrate, not
limit, the disclosure. Various parameters of the scientific methods
employed in these examples are described in detail below and
provide guidance for practicing the disclosure in general.
EXAMPLES
[0113] The disclosure demonstrates that a plasmid encoding for the
green fluorescent protein (Gfp) can be used as a reporter to
measure gene expression. This is a commonly used reporter-gene and
it enables a fast and convenient readout of the number of cells
that express the transgene by flow cytometry.
[0114] The data show that plasmid DNA can be absorbed onto hollow
Silica-NPs of 45, 80, and 120 nm size. Surface modifications that
increase the charge of the Silica-NPs are evaluated on all sizes to
determine if the DNA adsorption can be increased. To add additional
amine groups, the hollow Silica-NPs are functionalized with
3-aminopropyl (trimethoxy)silane. For example 1 mg of calcinated
hollow silica spheres, prepared from the 100 nm templates, are
suspended in 2 mL of 1% 3-aminopropyl(trimethoxy)silane acetone
solution. The mixture are stirred slowly for 2 hours with a
magnetic stirrer followed by collecting the particles by
centrifugation. The collected particles are washed with ethanol and
dried in vacuum for 24 hours at room temperature. Subsequently the
particles are heated at 450.degree. C. Surface modification by
adding poly-L-lysine are performed after the calcination process by
briefly incubating the particles in a 0.1% poly-L-lysine solution.
The solution phase size distribution of the nanoparticles also are
routinely monitored by dynamic light scattering (DLS) measurements.
This will give information on the dispersal state of the
nanoparticles just before their use in biological experiments. As
shown in the data different amounts of plasmid DNA are adsorbed to
titrated amounts of the different NPs to compare the efficacy of
complex formation and to identify the most effective silica-NP for
DNA adsorption. The complexes are resolved on a 1% agarose gel.
[0115] Gene expression: Once the optimal silica-NP surface
modification is determined, DNA is adsorbed to different sizes of
the NP (45, 80, and 120 nm) to determine which size confers the
strongest transgene expression. The rationale to compare different
sizes is that they could traffic differently, for example it is
possible that more of the smaller NPs translocate to the nucleus.
Immature human DCs are incubated with increasing doses of the
DNA-NP complexes as described in data using a plasmid that encodes
for gfp. 48 h after exposure to the DNA-NP complexes, Gfp
expression are analyzed by flow cytometry. Kinetics of transgene
expression as well as cell viability using propidium iodide
staining are determined by flow cytometry.
[0116] Peptide conjugation: To identify which surface modification
is best suited for peptide conjugation, fluorescently labeled
peptides (FITC on the N-terminus) are conjugated to the different
aminefunctionalized silica-NPs. The free C-terminus of the peptide
will form an amide bond with the amino groups on the silica-NPs
using EDAC as the coupling reagent. Only for the purpose of
demonstrating peptide binding to these surfaces will 1 .mu.m size
silica-NPs be used, as this allows for visualization and
quantification of the bound peptide by microscopy. Once the most
effective silica-NP modification for DNA and peptide binding is
identified, binding of peptides and DNA to the same 1 .mu.m size
silica-NPs is assessed. To determine co-localization FITC labeled
peptide and tetramethyl-rhodamine labeled-plasmid DNA are used and
analyzed by microscopy. Additionally adsorption of DNA to peptide
conjugated silica-NPs of different sizes by gel electrophoresis and
zeta potential measurements are taken. After demonstrating peptide
and DNA binding to the same particle by microscopy, the same
methods are used to generate smaller size multi-functional NPs (45,
80, and 120 nm) for the experiments listed below.
[0117] Generation of dendritic cells: To generate human DCs,
anonymous Buffy coats from healthy donors are purchased from the
San Diego Blood bank. DCs are prepared from peripheral blood
monocytes by culturing CD14+ monocytes in GM-CSF and IL-4 for 5 to
7 days, at which point they are immature DCs. To generate mouse
DCs, bone marrow-derived dendritic cells (BM-DC) are prepared from
C57/BL6 mice. Briefly, single bone marrow cell suspensions are
obtained from femurs and tibias, and then depleted of lymphocytes,
granulocytes, and Ia+ cells using a mixture of monoclonal
antibodies (anti-CD4, anti-CD8, anti-B220/CD45R, and anti-Ia) for
45 minutes on ice, followed by incubation with low-toxicity rabbit
complement for 30 minutes at 37.degree. C. Cells are resuspended at
a concentration of 10.sup.6 cells/ml in medium supplemented with
recombinant murine GM-CSF (10 ng/ml) and plated at 3 ml/well in
6-well plates. Floating cells are removed on days 3 and 5 of
culture by gentle pipetting and fed with fresh medium. On day 7,
the non-adherent and slightly adherent cells are collected for the
experiments. Further purification are achieved by positively
selecting CD11c+ cells using magnetic beads.
[0118] Testing activity of peptide-NP complexes: After
demonstrating Hp-91 peptide binding to the NPs by microscopy, the
DC-stimulatory function of the NP-bound peptides are evaluated on
both mouse and human DCs. During the maturation process DCs
up-regulate co-stimulatory and adhesion molecules and secrete large
amounts of inflammatory cytokines. Therefore, DC maturation can
easily be measured by flow cytometry looking at surface molecule
expression levels by ELISA measuring the amount of secreted
cytokines.
[0119] The immature human and mouse DCs are exposed to increasing
doses of silica-NP-Hp-91 complex, non-complexed silica-NP (negative
control), free Hp-91 peptide, or LPS as positive controls. Cell
culture supernatants are analyzed for the presence of inflammatory
cytokines by ELISA and changes in cell surface molecule expression
are monitored by flow cytometry. The same assays are used to
determine the extent to which CD40L plasmid DNA adsorbed to hollow
silica-NPs confers DC maturation.
[0120] Intracellular trafficking of the silica-NPs: If different
size silica-NPs confer different potentials for gene expression,
intracellular trafficking of the silica-NPs are analyze to
determine a possible mechanism. DCs are exposed to FITC-labeled NPs
of different sizes and harvested at different time points (30 min,
1 h, 2 h, 6, and 24 h) after exposure to the NPs. Cells are spun
onto glass slides and stained with Hoechst to visualize the nucleus
and determine the localization of particles in the nucleus. Cells
are stained with lysotracker (Molecular probes), which labels
endosomes and lysosomes as well as with an anti-LAMP1 antibody,
which reacts with a lysosomal protein. These experiments shed light
on whether particles of certain sizes or modifications get stuck in
lysosomes or whether they translocate to the nucleus. Furthermore,
to determine whether the NPs and DNA traffic together within the
cell or whether in certain intracellular milieus the DNA is
released from the NPs, tetramethyl-rhodamine-labeled-plasmid DNA
are adsorbed to FITC-labeled NPs and intracellular trafficking
kinetics are monitored by microscopy.
[0121] A higher density of positive charge on the NP surface is
expected to cause higher amounts of DNA adsorption. Thus, the NPs
with extra amine groups or with added poly-L-lysine adsorbed on the
surface are expected to bind more DNA. If both the DC-stimulatory
peptide and the CD40L plasmid confer similar DCs maturation
capacity.
[0122] 2 plasmids can also be adsorbed to the NPs, one encoding the
melanoma antigen and the other encoding CD40L as the DC stimulatory
molecule. Alternatively non-methylated CpG oligonucleotides, which
are also strong stimuli for DC activation, are adsorbed to the
NPs.
[0123] A MART1(=melanoma antigen)-expressing plasmid and a human
MART1-specific CD8+ T cell clone are used to evaluate the induction
of antimelanoma CTL responses. The size and surface modification of
Silica-NPs that enabled the most potent gene expression for human
DCs is used to adsorb a MART1-encoding plasmid and to covalently
attach the DC-stimulatory peptide Hp-91. Immature human DCs are
exposed to increasing doses of Silica-NP-complexes or non-complexed
NPs as control and subsequently cocultured with a CD8+
MART1-specific T cell clone. T cell activation will be measured by
IFN-.gamma. and granzymeB ELISPOT as well as in CTL assays.
[0124] Using the B16-OVA melanoma tumor model, multi-functional
silica-NPs carrying the OVA plasmid (as surrogate tumor antigen)
and Hp-91 are injected into mice before injection of B16-OVA tumor
cells to measure the prophylactic effect. To measure their
therapeutic potential, the complexes will be injected into tumor
bearing mice. In both settings the immunized mice are monitored for
the development of anti-OVA immune responses and for tumor
growth.
[0125] Human monocyte-derived DCs, for example, were generated from
PBMCs isolated from healthy donors by culturing adherent cells in
GM-CSF and IL-4 for 5 to 7 days. SiO.sub.2 nanoparticles were
generated using polymer beads as template and the surface was
functionalized with amino silane or amino phosphoric acid and the
polymer core was removed by calcination or organic solvents.
Several nanoparticles were synthesized: with non-modified surfaces,
functionalized with amine groups, or functionalized with
poly-L-lysine (pLL). DNA adsorption to the NPs was determined by
gel eletrophoresis. DNA adsorption to the NPs caused the DNA to be
retained in the well, whereas unbound DNA migrated into the gel. NP
uptake by DCs: DCs were incubated with NPs for 2 h in a 50 ul at
37.degree. C. Subsequently fresh media was added to the cells and
gene expression was analyzed 48 h later. Using these methods the
data indicated that silica-NPs can adsorb plasmid DNA. Surface
modifications including amine groups and poly-L-lysine (pLL) that
introduced additional positive charges were tested and lead to
increased DNA adsorption to the NPs. Furthermore, DNA could be
adsorbed to silica-NPs of different sizes (45, 80, and 120 nm).
[0126] To test uptake, immature DCs were exposed to FITC-labeled
NPs of 45, 100, and 200 nm diameter. All sizes were effectively
taken up by DCs and no obvious preference was observed. Both
unmodified and amine-modified NPs were taken up by DCs, but
pLL-modified NPs were not. Although the NPs were found
predominantly in the cytoplasm, confocal microscopy indicated that
NPs were also present in the nucleus of the DC. DCs loaded with NPs
showed high viability for at least 7 days, showing low toxicity
compared to other transfection methods. A plasmid that encodes for
gfp was used to demonstrate uptake by cells. The plasmid was
adsorbed to the 120 nm non-modified or amine modified-NPs. Immature
DCs were exposed to NP-DNA complexes and analyzed for Gfp
expression by flow cytometry. Using DNA complexes with amine
modified NPs 45% of the DCs expressed GFP at 48 h. DNA complexes
with un-modified NPs showed 50% reduced Gfp expression, which also
correlated with the fact that .about.50% less DNA was adsorbed. In
contrast to electroporation methods, no death of DCs and
.about.6-fold increase in the percentage of transfected DCs was
observed at 48 h.
[0127] These experiments demonstrate that SiO.sub.2-nanoparticles
of 80 and 120 nm are more efficient than electroporation to
introduce a transgene into DCs in vitro and possibly in vivo.
[0128] The data show that human immature DCs take up Silica-NP-DNA
complexes and express the transgene at 48 h. A MART1 (=melanoma
antigen)-expressing plasmid and a MART1-specific CD8+ T cell clone
are used to evaluate the induction of human anti-melanoma CTL
responses in vitro.
[0129] IFN-.gamma. ELISPOT: Hollow silica-NPs are adsorbed with
MART1-encoding plasmid (Silica-NP-MART1=negative control), CD40L
encoding plasmid (Silica-NP-CD40L=negative control), both plasmids
(Silica-NP-MART1/CD40L=new vaccine), the DC-stimulatory peptide
Hp-91 (Silica-NP-Hp-91=negative control), and MART1-encoding
plasmid plus Hp-91 (Silica-NP-MART1/Hp-91=new vaccine). Immature
human DC are incubated for 2 hours with the NP-DNA complexes and
respective controls listed above. 48 h and 72 h after NP exposure
the DCs are co-cultured with a CD8+ MART1-specific T cell clone for
24 h. As a positive control for T cell activation, the immature DCs
are exposed to LPS for 48 h and then pulsed with MART1 peptide
(ELAGIGILTV). T cell activation are measured by IFN-.gamma.
ELISPOT, which detects and quantified the number of IFN-.gamma.
secreting cells used as indication for T cell activation.
[0130] CTL assay: Immature human DC are incubated for 2 hours with
the NP-DNA complexes and respective controls listed above. 48 h and
72 h after NP exposure the DCs are co-cultured with a CD8+
MART1-specific T cell clone for 24 h. Subsequently the T cell clone
are evaluated for the ability to kill MART expressing target cells
in a CTL assay. As target cells antigen processing-deficient
HLA-A2.1+ T2 cells pulsed with the MART1 peptide (ELAGIGILTV) or
irrelevant 9mer peptides as a control are used. Prior to peptide
pulse, the target cells are labeled with the membrane dye PKH26
(red) and subsequently pulsed with 50 .mu.g/ml peptide for 2 h.
Cells are transferred (10.sup.4) to round-bottom 96-well plates and
varying numbers of CTLs are added. The co-cultures are incubated
for 4 h at 37.degree. C. At the end of the culture, the cell
viability are determined based on the mitochondrial trans-membrane
potential (.DELTA..PSI.m) using 3,3'-dihexyloxacarbocyanine iodine
(DiOC6) by flow cytometry. Live cells are DiOC6--bright, whereas
dying and dead cells are DiOC6--dim. OVA-specific killing of target
cells are calculated by gating on the red target cells using the
following equation: (% of DiOC6dim target cells pulsed with
peptide)-(% of DiOC6dim target cells pulsed without peptide). In
addition a Granzyme B ELISPOT assay are used to determine the
cytolytic potential of the activated T cells. This assay has shown
good correlation with Chromium release assays, but lacks the
radioactive hazard.
[0131] DCs exposed to Silica-NP-MART1, Silica-NP-CD40L, or
Silica-NP-Hp-91 are not expected to cause T cell activation. DCs
exposed to the multi-functional Silica-NP-MART1/CD40L as well as
the Silica-NP-MART1/Hp-91 are expected to cause strong T cell
activation.
[0132] Common mouse melanoma model will be used, where the melanoma
cell line B16-OVA are injected into mice. In this melanoma model,
the tumor cells express ovalbumin (OVA), which serves as surrogate
tumor antigen, allowing for the measurement of OVA-specific immune
responses. Thus a plasmid encoding OVA is used.
[0133] The Silica-NP size and composition that confers the
strongest T cell activation are used to generate multi-functional
NPs containing plasmid DNA that encodes for chicken ovalbumin
(OVA), together with CD40L plasmid or DC-stimulatory peptides. The
multi-functional NPs are evaluated in the in vivo model below in
both a prophylactic and therapeutic setting. Most vaccines using
"naked" DNA have shown promising results when injected i.m. Since
the goal is to target DCs, which is more likely to be achieved by
i.d. injection, the potency of the vaccines is compared when given
i.d. or i.m. The potency and type of immune responses has been
shown to correlate with protection from tumor growth and tumor
rejection. Therefore, the development of an immune responses as
well as tumor growth are measured in both the prophylactic and
therapeutic setting.
[0134] It is generally believed that for tumor rejection strong Th1
immune responses characterized by CD8 T cells secreting IFN-.gamma.
are required, whereas a Th2 response is thought to play a lesser
role. In order to gain a better understanding of the tumor
rejection mechanism cause by the multi-functional silica-NP
vaccine, further characterization of the type of immune response is
performed. In mouse, the production of antibody isotypes can be
used as a surrogate measurement for the type of immune response.
IgG2a is recognized as characteristic of a Th1 response, whereas
the production of IgG1 is characteristic of a Th2 response.
Therefore, the assessment of the type of immune response are done
by measuring IgG1, IgG2a and IgG2b levels by ELISA. The ratio of
IgG2a/IgG1 antibody titers are used as indicator of Th bias.
Furthermore, the secretion of cytokines also defines the type of
immune response. A Th2 response is characterized by the secretion
of Th2 type cytokines, such as IL-4, IL-5, whereas a Th1 type
response is characterized by the secretion of IL-2 and
IFN-.gamma..
[0135] IL-10 and TGF-.beta. are cytokines that contribute to
regulatory T cell responses, which interfere with tumor rejection.
Therefore, the secretion of these cytokines are measured by ELISA
as well.
[0136] Prophylaxis: Groups of mice will receive the
multi-functional silica NP vaccine first and then receive
injections of B16-OVA tumor cells. Half the mice from each group
are sacrificed to measure immune responses and the other half are
monitored for tumor growth. Groups of mice will receive i.d. or
i.m. injections of PBS, Silica-NP without DNA (neg. control),
Silica-NP with irrelevant DNA encoding for a non-mammalian antigen
e.g. firefly-luciferase (neg. control), Silica-NP-OVA/CD40L,
Silica-NP-OVA-Hp91, Silica-NP-OVA, Silica-NP-CD40L, and
Silica-NP-Hp91. Two doses of DNA 10 .mu.g and 50 .mu.g are
evaluated either adsorbed to NPs or as "naked" DNA. 10 .mu.g OVA
protein in IFA are injected as positive control. 7-14 days after
the first injection, mice will receive a booster injection
identical to the first injection. 10-14 days after the last
immunization, half of the mice from each group will receive s.c.
injections of 1.times.105 B16-OVA tumor cells and the other half
are sacrificed to measure the development of immune responses (see
below). The remaining mice are observed bi-weekly for tumor
appearance by palpitation. As primary measurement, the time to
tumor appearance in the treated groups compared to the PBS control
is monitored. As secondary measurement of tumor size using a set of
calipers is used. Tumors of at least 3 mm are scored. Mice are
sacrificed if tumors reach 1.5 cm in diameter or at week 6 after
injection of tumor cells, at which point all non-treated mice will
have developed tumors.
[0137] Therapeutic: Mice will receive s.c. injections of
5.times.105 B16-OVA tumor cells. Once the tumor reaches 3 mm in
size, mice will receive the same i.m. and i.d. injections of the
multi-functional silica NPs and controls as listed above. In both
settings, mice are divided randomly into groups (n=10) and, as
above, half the mice from each group are sacrificed 10-14 days
after the final injection to measure the development of immune
responses and the other half are monitored for tumor growth. To
measure the development of immune memory, mice that show complete
rejection of the tumor, are challenged with a second injection of
5.times.105 B16-OVA cells 1 month after the final injection of
multifunctional silica NPs.
[0138] Measurement of immune response: Groups of mice will receive
i.m. or i.d. injections as above. The in vivo induced T cell
responses are detected in vitro using a variety of assays. 1)
Proliferation assays are performed by adding OVA257-264 peptides
(to stimulate CD8 T cells) and OVA323-339 (to stimulate CD4 T
cells), PBS/no peptide (negative control) or ConA (positive
control) to unseparated splenocytes, which contain T cells and
antigen presenting cells, and measuring the uptake of
[3H]-thymidine after 4 d. 2) Cytokine secretion: To measure T cell
responses, unseparated splenocytes are set up as described above
but the positive control are phorbal myristate acetate (PMA) and
soluble anti-CD3, since ConA is not a very potent stimulus for Th2
cytokines. After 24 h, the culture supernatants are assessed for
IL-4, IL-2, IL-5, IL-10, TGF-.beta. and IFN-.gamma. levels by
ELISA. Furthermore, IFN-.gamma. ELISPOT are used to measure the
number of cytokine secreting T cells. To further investigate the
contribution of CD8+ and CD4+ T cells to the cytokine secretion,
either cell type are depleted from the splenocytes using specific
antibodies, prior to in vitro culture. 3) CTL assays: To expand
OVA-specific T cells from the spleens of the immunized mice, the
splenocytes are cultured in 24-well plates for 6 days at a
concentration of 3.times.10.sup.6 cells in 1.0 ml of medium with
the addition of recombinant mouse IL-2 (50 units/ml) after 24 h of
culture. Furthermore, a standard LDH release assay are performed at
day 6 to measure cytolytic activity, by incubating the splenocytes
with target cells pulsed with and without OVA peptide. The
absorbance values from supernatants are recorded at OD 490 nm. The
percent of specific lysis are calculated as follows:
(DExp.-ODSpon.E-ODSpon.T/ODMax.T.-ODSpon.T).times.100, where ODExp.
is the OD related to the experimental LDH relase, ODSpon.E. is the
OD related to the spontaneous release of LDH from the effector
cells only, ODSpon.T is the OD related to the spontaneous LDH
release from target cells only, and ODMaxT. is the OD related to
the maximum LDH release from target cells using lysis buffer.
[0139] In vivo immune response: To measure the immune responses
directly in vivo, transfer of 2.times.10.sup.6 OTI CD8+ T cells
into the mice is performed one day prior to immunization with the
silica-NP vaccines. These OTI CD8+ T cells are harvested from a T
cell receptor transgenic mouse (B6 background) which are specific
for Kb-SIINFEKL of OVA. Prior to injection, OT-I cells are labeled
with Carboxyfluorescein succinimidyl ester (CFSE), which consists
of a fluorescent molecule that stains the plasma membrane. During
each round of cell division, relative fluorescence intensity of the
dye is decreased by half, allowing us to examine cell division in
vivo. 3 days after injection of OT- cells, the animals are tested
for proliferation of OT-I cells by flow cytometry.
[0140] Toxicity: To monitor for potential pathological effects of
the silica-NP vaccines, the spleen, liver and kidney are collected
at time of euthanasia. The organs are weighed and additional tissue
analysis are performed.
[0141] Mice that are immunized with DNA-NP-Hp-91-complexes are
protected from tumor growth and reject the established tumor
cells.
[0142] The effectiveness of the new silica-NP complexes in inducing
melanoma-specific CTL are determined on a quantitative basis as
follows: a). In vitro experiments: The target cells are incubated
with decreasing concentrations of the OVA-derived peptides or
corresponding nanoparticle based vaccines. Values obtained from the
LDH-release assays and ELISPOT assays are used to construct
dose-response curves and these are compared. IC50 values from a
minimum of 5 independent experiments are compared for statistical
significance using the Student t test. b).
Example 1
[0143] Preparation of the solution of hydrolyzed
tetramethoxysilane. 14.0 mL tetramethoxysilane is added to 100 mL
0.01 M hydrochloric acid. The mixture is stirred at room
temperature for 15 minutes. The solution is to be used as the
precursor to deposit silica shells directly.
Example 2
[0144] Synthesis of core-shell silica spheres with 100 nm amine
polystyrene beads. 4.0 mL of 2.6% w/v 100 nm sized amine
polystyrene beads, 16 mL of 0.1% poly-L-lysine solution and 75 mL
of 0.1 M phosphate buffer are mixed in a 150 mL pear-shaped flask.
2 mL of hydrolyzed tetramethoxysilane is added and the mixture is
stirred vigorously with a vortex agitator at a speed of 3000 rpm.
The stirring lasts 5 minutes at room temperature and the mixture is
transferred into two 50 mL centrifuge tubes. A white precipitate is
collected by centrifugation. The core-shell particles are suspended
in deionzed water and stirred with the vortex agitator for 5
minutes and then spun down again by centrifugation. The washing
procedure is repeated one more time followed by washing with
ethanol. 185 mg Core-shell particles are dried in vacuum at
60.degree. C. for 48 hours.
Example 3
[0145] Synthesis of core-shell silica spheres with 200 nm amine
polystyrene beads. The synthesis procedure is similar to example 2,
except that the 100 nm amine polystyrene beads are replaced by 200
nm amine polystyrene beads.
Example 4
[0146] Synthesis of titania core-shell silica spheres with 200 nm
amine polystyrene beads. 2.0 mL of 2.6% w/v 100 nm sized amine
functionalized polystyrene beads and 80 mL of absolute ethanol are
mixed in a 150 mL pear-shaped flask. 2.0 mL of 1 M titanium
t-butoxide/ethanol solution is added and the mixture is stirred
vigorously with a vortex agitator at a speed of 3000 rpm. The
stirring lasts 2 minutes at room temperature and the mixture is
transferred into two 50 mL centrifuge tubes. A white precipitate is
collected by centrifugation. The core-shell particles are suspended
in absolute ethanol and stirred with the vortex agitator for 5
minutes and then spun down again by centrifugation. The washing
procedure is repeated one more. 120 mg Core-shell
polystyrene/titania particles are dried in vacuum at 60.degree. C.
for 48 hours.
Example 5
[0147] Removing polymer cores by calcination. 10 mg of dry
core-shell silica particles are placed in a furnace and the
temperature is raised at a speed of 5.degree. C./min to 450.degree.
C. The core-shell particles are calcinated in air at 450.degree. C.
for 4 hours and the temperature is then cooled at a speed of
5.degree. C./min until it reaches room temperature. 3.2 mg of final
product of hollow silica spheres is obtained as a white powder.
Yield is nearly quantitative based on the number of template
spheres.
Example 6
[0148] Removing polymer cores by dissolution in toluene. 10 mg of
dried core-shell spheres are suspended in 20 mL of toluene and the
mixture is stirred with a magnetic stirrer for 1 hour. The solid is
collected by centrifugation. The washing procedure is repeated
three more times followed by drying the particles in vacuum at
60.degree. C. for 48 hours. 3.7 mg of hollow silica spheres is
obtained as white powder. Some residual polystyrene is still
evident from the infra-red spectra. The TEM photographs of this
material show thicker shell walls, presumably from adsorbed
polystyrene on the silica walls.
Example 7
[0149] Removing cores by dissolution with added ethylene diamine.
10 mg of dried core-shell spheres are suspended in a mixture of 5
mL of ethylene diamine and 15 mL dichloromethane and stirred with a
magnetic stirrer for 1 hour. The solid is collected by
centrifugation. The washing procedure is repeated three more times
followed by drying the particles in vacuum at 60.degree. C. for 48
hours. 3.5 mg of hollow silica spheres is obtained as white powder.
Compared to Example 5 nearly all the polystyrene core is removed by
this method.
Example 8
[0150] Functionalized the hollow silica spheres with 3-aminopropyl
(trimethoxy)silane. 1 mg of calcined hollow silica spheres,
prepared from the 100 nm templates, are suspended in 2 mL of 1%
3-aminopropyl(trimethoxy)silane acetone solution, The mixture is
stirred slowly for 2 hours with a magnetic stirrer followed by
collecting the particles by centrifugation. The collected particles
are washed with ethanol and dried in vacuum for 24 hours at room
temperature.
TABLE-US-00001 TABLE 1 Size of hollow silica spheres isolated and
its dependence on the size of the templates and the methods of
removing the polystyrene cores. Size of template (nm) 100 200 500
Diameter of core-shell spheres (nm) 126.+-. 210 .+-. 6 454 .+-. 16
Diameter of hollow spheres after 126 .+-. 7 205 .+-. 7 443 .+-. 21
calcinations (nm) Diameter of hollow spheres after 102 .+-. 8 188
.+-. 9 397 .+-. 15 dissolution (nm)
Example 9
[0151] Uptake of silica-NPs by dendritic cells. Immature human DCs
were incubated with FITC-labeled core-shell silica-NPs to determine
cellular uptake. FITC labeled polystyrene cores were used as
templated to generate a silica shell. Immature DCs were exposed to
200 nm silica NPs for 2 h and an image was taken in the tissue
culture plate of live cells (FIG. 9 left image). All cells had
taken up silica-NPs. The experiment was repeated and 6 h after
exposure to the NPs, DCs were collected and spun onto glass slides
using a cyto-centrifuge. In order to determine whether the NPs
localize to the cell nucleus, the cells were fixed and the nuclei
were stained using the nuclear dye Hoechst. The slides were
analyzed by confocal microscopy (FIG. 9, right image). A few NPs
were found to be localized in the nuclei (see white arrows) already
at the 6 h time point. Later time points will be investigated.
Example 10
[0152] Adsorption of plasmid DNA to hollow Silica-NPs. Hollow
solvent extracted Silica-NPs were resuspended in PBS and sonicated
for 15 min. Different amounts of Silica-NPs were diluted in 700 mM
NaCl and the dilution was mixed at 10 .mu.l per minute with equal
volume of a plasmid dilution under constant vortexing, with a total
of 50 .mu.l NP dilution and 50 .mu.l of the DNA. After formation of
the complexes, 10 .mu.l of the mixture was resolved on a 1% agarose
gel (FIG. 6). DNA adsorption to the Silica-NPs prevents the DNA
from running into the gel. Instead, the DNA stays in the wells with
the Silica-NPs (FIG. 6 lanes 7-14), whereas free unbound plasmid
runs as two bands (FIG. 6 lanes 1 and 2). A dose response of DNA
adsorption to increased amounts of NPs was observed. 2 .mu.g
plasmid DNA were completely adsorbed by 50 .mu.l of a 0.95 mg/ml
Silica-NP solution. Some free plasmid was observed when 50 .mu.l of
a 0.48 mg/ml NP solution were used. 6 mg of plasmid were completely
adsorbed by 50 .mu.l of a 3.8 mg/ml NP solution. NPs were analyzed
to determine if they could be functionalized for enhanced DNA
adsorption.
[0153] A comparison of unmodified hollow silica-NPs and modified
hollow silica-NPs with additional surface amine groups (+NH2) (FIG.
10A). These hollow Silica-NPs were functionalized with
3-aminopropyl (trimethoxy) silane as in Scheme II to add the
additional amine groups. Amine-modified hollow silica NPs were able
to almost completely adsorb 2 .mu.g of plasmid DNA when using 50
.mu.l of a 0.48 mg/ml NP solutions (FIG. 10A right gel: lane 4),
whereas free plasmid DNA was detected when using the same amount of
unmodified silica NPs (FIG. 10A left gel: lane 4). Thus, the
addition of amine groups enhanced DNA adsorption. Although the
solvent extraction procedure removes 75% of the polystyrene core,
to prevent toxicity in vivo, the hollow silica NPs were burned at
high heat (calcination) to completely remove any residual
polystyrene. The burned hollow silica NPs with different
modifications were compared for their DNA adsorption capacity (FIG.
10B). Interestingly, burned unmodified NPs bound very little, if
any DNA (FIG. 10B, left gel), whereas the solvent extracted
unmodified NPs effectively adsorb DNA (FIG. 10A left gel). The
burning process removes the poly-Lysine chains that remained on the
silica shell from the templating technique and thus removes the
positive charges that allow DNA adsorption. Modified silica-NPs
with additional poly-L lysine (pLL) on the surface of burned NPs
was the most potent for DNA adsorption, even 6 .mu.g plasmid DNA
was completely adsorbed by 50 .mu.l of 0.95 mg/ml NPs (FIG. 10B,
right gel). The amine modified silica-NPs only contain short
positively charged chains (see Scheme II), whereas poly-L lysine
are long chains with many amine groups. Therefore poly-L lysine
coating allows for more charge-charge interactions between the NP
and the DNA and therefore stronger binding capacity. The ability of
different size solvent extracted unmodified hollow silica-NPs to
adsorb DNA (FIG. 10C) were compared. Although all sized were able
to adsorb DNA, larger 120 nm NPs showed increased DNA
adsorption.
Example 11
[0154] Hollow silica-NP-DNA complexes are stable. Since the
complexes were generated in the presence of 700 mM NaCl and the
physiological salt concentration is 150 mM, the salt was exchanged
with media prior to exposure of DCs to reduce toxicity. The
Silica-NP-DNA complexes were sonicated for 15 min, spun down at
6000 rpm for 10 minutes, and resuspended in culture media. To test
whether the plasmid would be released from the Silica-NPs during
these steps, aliquots were taken before sonication, post
sonication, from the supernatant after the spin, and from the
resuspended pellet (FIG. 7). At all stages of the process the
plasmid DNA remained adsorbed to the Silica-NPs and thus in the
wells of the gel, indicating that neither sonication nor spinning
caused a release of the plasmid DNA from the Silica-NPs. Both
unmodified (U) and amine-modified (C) NPs showed the same
result.
Example 12
[0155] Preparation of Silica-Iron Ethoxide Precursor.
[0156] 25 mg of iron (III) ethoxide is dissolved in 1 mL of
absolute ethanol. The solution is then filtered using a 0.22 .mu.m
syringe microfilter to remove any solids. 10 .mu.L of the iron
(III) ethoxide solution is then added to 25 .mu.L of hydrolyzed
tetramethoxysilane and vortexed for 30 seconds to give a
homogenous, translucent orange solution.
[0157] Synthesis of Iron Doped Hollow Silica Spheres with 200 nm
Amine Polystyrene Beads.
[0158] To 50 .mu.L of 2.5% w/v 200 nm amine polystyrene beads was
added to 1 mL of an alcohol, either methanol or ethanol, in a 2 mL
eppendorf tube. The beads were suspended and 200 .mu.L of 0.1%
poly-L-lysine solution was added and the solution was mixed for 1
minute. 35 .mu.L of the silica-iron ethoxide precursor was then
added and the solution stirred at 3000 rpm on a vortex agitator for
60 minutes at room temperature. The yellow-orange colloid is then
collected via centrifugation. The supernatant is removed and 1 mL
of deionized water is added. The precipitate is resuspended in the
water using a vortex and collected again using centrifugation. The
washing step is repeated two more times and then the precipitate is
dried in a vacuum oven at 50.degree. C. for 24 hours. The dried
precipitate is then calcined at 500.degree. C. for 48 hours to
remove the polystyrene core. Up to 10% iron incorporation is
observed by EDAX in the SEM photomicrographs, which may impart
biodegradability over the long term.
[0159] Synthesis of Hollow Silica Spheres with Encapsulated
Magnetic Iron Oxide Nanoparticles Using 200 nm Amine Polystyrene
Beads.
[0160] To 50 .mu.L of 2.5% w/v 200 nm amine polystyrene beads was
added to 500 .mu.L of a 5% dichloromethane ethanol solution (v/v)
in a 2 mL eppendorf tube and suspended using a vortex agitator. 10
.mu.L of 1.4% (w/v) magnetic iron oxide nanoparticles (5 nm) were
then added to the solution and mixed for 30 seconds. The beads were
allowed to swell in the solvent for 2 hours, with 10 second
agitation occurring every 20 minutes. 750 .mu.L of methanol was
then added and the solution mixed and allowed to sit at room
temperature for 12 hours. The solvent was reduced to a volume of
250 .mu.L, and 750 .mu.L of 0.1M phosphate buffer solution was
added and the solution mixed. 200 .mu.L of 0.1% poly-L-lysine
solution was added and the solution was mixed for 1 minute. 25
.mu.L of 1M hydrolyzed tetramethoxysilane was then added and
stirred at 3000 rpm on a vortex agitator for 10 minutes. The
orange-brown precipitate is then collected in the tube using a
magnet. The supernatant along with any non-magnetic particles are
removed and 1 mL of deionized water is added. The precipitate is
resuspended using a vortex agitator and then recollected using
centrifugation. This process is repeated two more times and the
precipitate is dried in a vacuum oven at 50.degree. C. for 24
hours. The dried precipitate is then calcined at 500.degree. C. for
48 hours to remove the polystyrene core. This permits magnetic
manipulation of the silica nanospheres.
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[0162] Although a number of embodiments and features have been
described above, it will be understood by those skilled in the art
that modifications and variations of the described embodiments and
features may be made without departing from the teachings of the
disclosure or the scope of the invention as defined by the appended
claims.
* * * * *