NZ616780B2 - A method for the treatment of a solid tumour - Google Patents
A method for the treatment of a solid tumour Download PDFInfo
- Publication number
- NZ616780B2 NZ616780B2 NZ616780A NZ61678012A NZ616780B2 NZ 616780 B2 NZ616780 B2 NZ 616780B2 NZ 616780 A NZ616780 A NZ 616780A NZ 61678012 A NZ61678012 A NZ 61678012A NZ 616780 B2 NZ616780 B2 NZ 616780B2
- Authority
- NZ
- New Zealand
- Prior art keywords
- particulate material
- stabiliser
- steric
- tumour
- use according
- Prior art date
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Classifications
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- A61K31/495—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins having six-membered rings with two or more nitrogen atoms as the only ring heteroatoms, e.g. piperazine or tetrazines
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Abstract
Disclosed herein is the use of two separate formulations of a particulate material, and a cellular toxin, effective to penetrate a solid tumour and induce cytotoxicity, in the manufacture of a medicament for the treatment of a solid tumour, wherein said particulate material is in the form of a dispersion in a liquid carrier, the particulate material being maintained in the dispersed state by a steric stabiliser; wherein said steric stabiliser comprises an anchoring portion and a steric stabilising polymeric segment, wherein the anchoring portion is different from the steric stabilising polymeric segment; and wherein the anchoring portion has an affinity towards the surface of the particulate material and secures the stabiliser to the particulate material. rsion in a liquid carrier, the particulate material being maintained in the dispersed state by a steric stabiliser; wherein said steric stabiliser comprises an anchoring portion and a steric stabilising polymeric segment, wherein the anchoring portion is different from the steric stabilising polymeric segment; and wherein the anchoring portion has an affinity towards the surface of the particulate material and secures the stabiliser to the particulate material.
Description
A METHOD FOR THE TREATMENT OF A SOLID TUMOUR
. 1 -
A METHOD OF TREATMENT AND AGENTS USEFUL FOR SAME
FIELD OF THE ION
The present invention relates generally to a method of treating a neoplastic condition
and to agents useful for same. More ularly, the present invention is directed to a method
of facilitating the treatment of a solid tumour in a sed manner via. the co-administration of
particulate material and a cellular toxin. The method of the present invention is useful in a
of primary and metastatic s.
range of therapeutic treatments including the treatment
l0 BACKGROUND OF THE INVENTION
Bibliographic details of the ations referred to by the author in this
specification are ted alphabetically at the end of the description.
The reference in'this specification to any prior publication (or ation derived
from it), or to any matter which is known, is not, and should not be taken as an
‘ ledgment or admission or any form of suggestion that that prior publication (or
information derived from it) or known matter forms part of the common general knowledge in
the field of endeavour to which this specification relates.
Malignant tumours, or cancers, grow in an uncontrolled manner, invade normal tissues,
and often metastasize and grow at sites distant from the tissue of origin. In general, cancers
are derived from one or only a few normal cells that have undergone a poorly understood
process called malignant transformation. Cancers can arise from almost any tissue in the body.
Those derived from epithelial cells, called carcinomas, are the most common kinds of cancers.
Sarcomas are malignant tumours of mesenchymal tissues, arising from cells such as
fibroblasts, muscle cells, and fat cells. Solid malignant tumours of lymphoid tissues are called
lymphomas, and marrow and blood-borne malignant tumours of lymphocytes and other
hematopoietic cells are called leukaemias.
Cancer is one of the three leading causes of death in industrialised nations. As
treatments for infectious es and the prevention of cardiovascular disease ues to
improve, and the average life expectancy ses, .cancer is likely to become the most
common fatal disease in these countries. ore. successfully treating cancer requires that
cells be removed or destroyed without killing the An ideal way to
. all the malignant patient.
achieve this would be to induce an immune response against the tumour that would
W0 2012/142669
discriminate between the cells of the tumour and their normal cellular counterparts. r,
immunological approaches to the treatment of cancer have been attempted for over a century
with unsustainable results.
Accordingly, current methods of treating cancer continue to follow the long used
protocol of surgical excision (if possible) followed by radiotherapy and/or chemotherapy, if
ary. The success rate of this rather crude form of treatment is extremely variable but
generally decreases significantly as the tumour becomes more advanced and metastasises.
Further, these treatments are associated with severe side effects ing disfigurement and
scarring from y (cg. mastectomy or limb amputation), severe nausea and vomiting from
chemotherapy, and most significantly, the damage to normal tissues such as the hairfollicles,
gut and bone marrow which is induced result of the relatively nonospecific targeting ‘ as a
mechanism of the toxic drugs which form part of most cancer treatments and is a major
limiting factor for dosage
Still further, common chemotherapy drugs do not significantly penetrate into tissue
further than about 70 microns from the blood supply (Primeau er 0]. Clin. Cane. Res. 2005,
llz8782-8788; nton et al. Nat. Rev. Cancer‘ 2006, 6:583-592). The rapid growth and
poor vascular development of most solid tumours puts many tumour cells well beyond the
capacity of the drugs to penetrate the tissue. Critically, many cells experience sub-lethal doses.
allowing them to survive and to develop drug resistance.
Solid tumours cause the greatest number of deaths from cancer and mainly comprise
tumours of the linings of the bronchial tree and the alimentary tract that are knOWn as
carcinomas. in the year 2000 in Australia. cancer ted for 30% of male deaths and 25%
of female deaths r in Australia 2000, 2003) and it accounted for 24% of male and 22%
of female deaths in the US in year 2001 (Arias et a1. 2003,.Naliona! Vital Statistics Reports
52:|1 l-llS). Solid tumours are not usually curable once they have spread or ‘metastasised’
hout the body. The prognosis of atic solid tumours has improved only marginally
in the last 50 years. The best chance for the cure of a solid tumour remains in the use of local
treatments such as surgery and/or radiotherapy when the solid tumour is sed to its
originating lining ~and has not spread either to the lymph nodes that drain the tumour or
elsewhere. Nonetheless, even at this early stage, and particularly if the tumour has spread to
the draining lymph nodes, microscopic deposits of cancer known as etastases may have
y spread throughout the body and will subsequently lead to the death of the patient. In
WO 42669
this sense. cancer is a systemic disease that requires systemically stered treatments. Of
the patients who receive surgery and/or herapy as definitive local treatment for their
primary tumour and who have micrometastases, a minor proportion may be cured or at least
achieve a durable remission from cancer by the addition of adjuvant systemic ents such
I '
as cytotoxic chemotherapy er hormones.
Conventionally, solid cancer has been treated locally with surgery and/or radiotherapy,
and during its metastatic stage with systemically administered cytotoxic drugs, which often
interfere with the cell cycle of both normal and malignant cells. The relative selectivity of this
approach for the treatment of malignant tissues is based to some extent on the more rapid
of
recovery of normal tissues from xic drug damage. More recently, the targeted therapy
cancer has aimed to improve the therapeutic ratio of cancer treatment by enhancing its
specificity and/or precision of delivery to malignant tissues while minimising adverse
consequences to normal non-malignant tissues. Two of the major classes of targeted therapy
are (i) the small molecule tors such as the tyrosine kinase inhibitors imatinib mesylate
(Glivece’), ib a®) and erlotinib (Tarceva®), and (ii) the monoclonal antibodies
(mAb) such as rituximab (Mabthera®) and trastuzumab (Herceptin®).
in parallel to the development of targeted therapies, combining at least two
conventional anti-cancer treatments such as chemotherapy and radiotherapy in novel ways has
been another approach to the development of cancer eutics. By ting synergistic
interactions between the different modalities of treatment, ed modality ent seeks
to improvo treatment efficacy so that the therapeutic. ratio for the combined treatment is
superior to that for each of the individual treatments.
Combined» modality treatment using external beam radiation and radiosensitising
chemotherapeutic drugs such as 5-fluorouracil and cisplatin (chemoradiotherapy) has
improved survival in a number of solid tumours such as those of head and neck, lung,
oesophagus, stomach, pancreas and rectum because of both ed local tumour control and
reduced rates of distant failure (TS ce. Oncology (Humington) 17:23—28. 2003).
Although radiosensitising drugs increase tumour response, they also increase toxicity to
adjacent normal tissues, which is ally true of the potent new generation radiosensitisers,
gemcitabine and docetaxel. However, decreasing the ion volume allows cytotoxic doses
of gemcitabine to be better tolerated clinically (Lawrence 2003, supra). adiotherapy
may overcome mutually reinforcing resistance mechanisms, which may only manifest in vivo.
PCT/AU2012l000414
Radioimmunotherapy (RlT) is a systemic treatment that takes age of the
specificity and avidity of the antigen-antibody interaction to deliver lethal doses of radiation to
cells that bear the target antigen. Radio-isotopes that emit B-particles (e.g. 13‘Iodine, ”Yttrium.
'88%enium, and 67Copper) are usually used to label monoclonal antibodies (mAb) for
eutic applications. The energy from B-radiation is released at relatively low intensity
over distances measured in millimeters (Waldmann, Science 252:1657-l662, l991; Bender er
al., Cancer Research 52:121-126, 1992; O'Donoghue el al. Journal of Nuclear Medicine
36:]902-1909, I995; hs et al. International Journal of Cancer 81:985—992, 1999). Thus,
nergy B-emitters such as ium are useful for the treatment of larger and
heterogeneous solid tumours (Liu er al. Bioconjugaie try 12:7—34. 200i). Research
interest‘in radioimmunotherapy has been reawakened because in spite of the low radiation
doses delivered, significant and cted ical effects of Ri'f upon surrounding host
cells have been observed (Xue er al. Proceedings of the National Academy of es of the
United States of America 9921376543770, 2002). Furthermore, the lower but biologically
effective dose of radiation delivered by RIT had greater cytocidal effects than a larger dose of
radiation conveyed as external beam radiotherapy hova et al., PNAS l0] :l4865-l4870,
2004). Nonetheless, the efficiency of RlT as a treatment for solid tumours may be hampered
by the low penetration of antibody through the tissue barriers that surround the target antigen
in the tumour, which will uently extend circulatory half life of the antibody (Britz-
Cunningham er al. Journal of Nuclear Medicine 44:]945-1961, 2003). Furthermore, RIT is
often impeded by the heterogeneity of the target antigen’s expression within the tumour. Thus,
gh RlT affords lar ing of tumour cells. the major limitation of RlT remains
the toxicity that may result from large .doses of radiation that are delivered systemically in
order to achieve sufficient targeting —Cunningham et al. 2003. supra; Christiansen et al.
' Molecular Cancer Therapy 3:]493-1501, 2004). Altogether, a useful therapeutic index using
Rl'l‘ has proven difficult to achieve clinically (Sellers 2! al. Journal of Clinical investigation
104:1655-1661, 1999).
Tumour associated antigens, which would allow differential targeting of tumours.
while sparing normal cells, have also been the focus of cancer research. gh abundant
ubiquitous antigens may provide a more concentrated and accessible target for RlT, studies
adopting this have been extremely limited.
The development of nanoparticle technology was also hailed as an exciting new
W0 20 669
frontier in terms of the development of new and effective cancer treatments. However,
although previous attempts at using particulate material, such as nanoparticles, to target
s for either diagnostic or therapeutic purposes have been extensive.
in the context of
therapeutics there has. disappointingly, been minimal success. With stics. relatively
shallow ation of the particles into the tumour has been sufficient to achieve the objective
of visualising the tumour. However, in terms of the delivery ofa therapeutic agent, such
shallow penetration has not been sufficient to ively deliver the agent throughout the
tumour, in particular to the interior of the tumour, as is required if tumour destruction is to
be achieved. in relation to therapeutics, specifically, conjugation of particles to a wide variety
of different materials has so far failed to live up to the promise of achieving effective tumour
penetration, this being an essential prerequisite for a therapeutic to have any chance of
iveness.
Significant effort has also been made to take advantage of the enhanced permeability
and retention (EPR) effect of tumours as a means to develop an ive therapeutic. t
limiting the present invention to any one theOry or mode of action, this is a well described
phenomenon based on the notion that certain sizes of molecules, typically liposomes or
macromolecular drugs, tend to preferentially accumulate in tumour tissue. The general
explanation for this phenomenon is that. in order fdr tumour cells to grow quickly, they must
stimulate the production of blood vessels. VEGF and other growth factors are involved in
cancer angiogenesis. Tumour cell aggregates of sizes as small as l50-200um become
dependent on blood supply carried by neovasculature for their nutritional and oxygen supply.
These newly formed tumour vessels are usually al in form and ecture. They
comprise -aligned defective endothelial cells with wide fenestrations, lacking a smooth
muscle layer, or innervation with a wider lumen, and impaired functional receptors for
angiotensin 11. Furthermore, tumour tissues usually lack effective lymphatic drainage. All
' these factors will lead to abnormal molecular and fluid transport cs, especially for
macromolecular drugs. Accordingly, it has been thought that one way to achieve ive
drug targeting to solid tumours is to exploit these abnormalities of tumour vasculature in terms
of active and selective delivery of anticancer drugs to tumour tissues, notably defining the EPR
effect of macromolecular drugs in solid tumours. Due to their large lar size, nanosized
macromolecular anticancer drugs administered intravenously escape renal clearance. Often
they cannot penetrate the tight endotheiial junctions of normal blood vessels, but they can
WO 42669
extravasate in tumour vasculature and become trapped in the tumour vicinity. Nevertheless,
the EPR effect has not been efficiently or successfully harnessed.
Various rticles have been designed which are directed to ing efficient
ar endocytosis. However, even if this is achievable, the issue of tissue penetration is still
The general notion of the
a separate one which, to date, has not been successfully overcome.
use of a nanoparticle as a vector for delivery of a drug is widely sed in the literature but.
in the absence of achieving deep tumour penetration, is of limited value.
Even where effective tumour distribution of a drug is achieved (by whatever means) a
further problem has been the fact that neoplastic cells within solid tumours can exhibit a
slowed metabolism. This means that even if a cytotoxic drug ates to these cells. if it is
not effectively metabolised'it will have a limited impact on the viability of the tumOur.
Accordingly, there is an urgent and ongoing need to develop ed systemic
therapies for solid cancers, in particular metastatic cancers.
In work leading up to the present invention it has been determined that particulate
material which is ined in a sed state by a stabiliser is able to achieve deeper
penetration into solid tumour models than has previously been achievable using nanoparticle
technology. This has enabled the development of an effective means for treating solid
tumours, both primary and metastatic, based on the co-administration of a cellular toxin with
the particulate material. By either sequentially or simultaneously delivering this toxin, deeper
ation and therefore more extensiVe cellular exposure to the toxin is achieved. By virtue
of the less effective reticuloendothelial clearance which is associated with s, a form of
targeted treatment is effectively achieved. Still r, it has been observed that the toxin
uptake by tumours penetrated by the particles of the present invention is effective, suggesting
upregulation of tumour cell metabolism. Accordingly, the method of the present invention
provides a means for achieving a more effective localised delivery and uptake of a- cellular~
toxin to a tumour and its metastases in a manner which is characterised by significantly
ed outcomes and/or d side effects ve to those which would'normally be
expected in the context of conventional treatment of an equivalent type of tumour. This is an
extremely significant development since current protocols directed to treating metastatic
disease are based on the non-targeted systemic delivery of chemotherapeutic agents.
W0 2012/142669
SUMMARY OF THE INVENTION
Throughout this specification and the claims which follow. unless the t es
ise, the word “comprise”, and variations such as “comprises" and “comprising", will be
understood to imply the inclusion of a stated r or step or group of integers or steps but
not the exclusion of any other integer or step or group of integers or steps.
As used herein, the term “derived from” shall be taken to indicate that a particular
integer or group of integers has originated from the species specified. but has not necessarily
been obtained directly from the Specified source. r. as used herein the singular forms of
“a”, “and" and “the” include plural referents unless the context clearly dictates otherwise.
' Unless ise d, all technical and scientific terms used herein have the same
meaning as commonly understood by one of ordinary skill in the art to which this invention
belongs.
One aspect of the present invention is directed to a method of treating a solid tumour in
a subject, said method comprising co-administering to said subject an effective amount of
particulate material and a\celiular toxin for a time and under conditions sufficient to facilitate
distribution of said particulate material and toxin to said tumour wherein:
(i) said particulate material is administered in the form ofa dispersion in a liquid carrier,
the particulate material being maintained in the dispersed state by a stabiliser; and
(ii) said stabiliser comprising an anchoring portion that (a) anchors the iser to the'
particulate material, and (b) is different from the remainder of the iser;
and wherein said particulate materiai and toxin penetrate said solid tumour.
For ience, said particulate material that is maintained in the dispersed state by a
stabiliser may herein be referred to as lised particulate material".
In one embodiment, the stabiliser is a steric stabiliser, said steric stabiliser comprising
a steric ising polymeric segment and an anchoring portion, wherein the steric stabilising
polymeric segment is different from the anchoring portion. and wherein the anchoring portion
anchors the stabiliser to the particulate material
The method may ore comprise co-administering to said subject an effective
amount of particulate al and a cellular toxin for a time and under conditions sufficient to
facilitate distribution of said particuiate material and toxin to said tumour wherein:
(i) said particulate al is administered in the form of a dispersion in a liquid carrier,
the particulate material being maintained in the dispersed state by a steric stabiliser;
2012/000414
(ii) said steric stabiliser Comprising a steric stabilising polymeric segment and an
anchoring portion, wherein the steric stabilising polymeric segment is different from
the anchoring portion, and wherein the anchoring portion s the stabiliser to the
particulate material;
and wherein said particulate al and toxin penetrate said solid tumour.
In r embodiment, said solid tumour is benign.
In a further embodiment said tumour is malignant.
in yet r embodiment, said anchoring portion is an anchoring ric segment.
In that case, said stabiliser comprises an anchoring polymeric segment, or said steric stabiliser
comprises a steric stabilising polymeric segment and an anchoring polymeric segment;
in a further embodiment, said stabiliser comprises an anchoring portion, one or both of
the stabiliser or anchoring portion being derived from one or more ethylenically unsaturated
monomers that have been polymeriscd by a living polymerisation que, wherein the
anchoring portion is different from the remainder of the stabiliser, and wherein the anchoring
portion anchors the iser to the particulate material. According to this embodiment, the
anchoring portion may be referred to as an anchoring polymeric segment.
In another ment, said steric iser comprises a steric ising polymeric
segment and an anchoring polymeric segment, one or both of which are derived from one or
more ethylenically unsaturated monomers that have been polymerised by a living
polymerisation technique, wherein the steric stabilising polymeric segment is different from
the anchoring polymeric segment, and wherein the anchoring polymeric segment anchors the
stabiliser to the particulate al.
In another aspect the present invention provides a method of treating a malignant solid
tumour in a subject, said method comprising co-administering to said t an effective
amount of particulate material and a ar toxin for a time and under conditions sufiicienl to
facilitate distribution of said particulate al and toxin to said tumour wherein:
(i) said particulate material is administered in the form of a dispersion in a liquid carrier,
the ulate al being maintained in the dispersed state by a iser; and
(ii) said stabiliser comprising an anchoring portion that (a) anchors the stabiliser to the
particulate material. and (b) is different from the remainder of the stabiliser;
and wherein said particulate material and toxin penetrate said solid tumour.
Where the stabiliser is a steric stabiliser comprising a steric stabilising polymeric
segment and an anchoring portion, wherein the steric stabilising polymeric segment is different
W0 2012/142669
from the ing portion, the method of treating a malignant solid tumour in a subject
comprises co-administering to said subject an effective amount of particulate material and a
cellular toxin for a time and under conditions sufficient to facilitate distribution of said
particulate material and toxin to said tumour wherein:
(i) said partiCulate material is administered in the form of a dispersion in a liquid carrier,
the particulate material being maintained in the dispersed state by a steric stabiliser;
(ii) said steric stabiliser comprising a steric stabilising polymeric segment and an
anchoring portion, n the steric stabilising polymeric segment is different from
the anchoring portion, and wherein the anchoring portion anchors the stabiliser to the
particulate material;
and wherein said particulate material and toxin ate said solid tumour.
In one ment, said malignant solid tumour is a metastatic malignant solid
tumour. Reference to “metastatic” should be understood as a reference to a tumour which
either has one metastatisation or may have one metastatisation.
In another embodiment, said malignant solid tumour is a central s system
tumour. retinoblastoma, neuroblastoma, paediatric tumour, head and neck cancer such as
squamous cell cancer, breast and prostate cancer, lung , kidney cancers, such as renal
cell adenocarcinoma, oesophagogastric , hepatocellular oma, pancreaticobiliary
neoplasia, such as adenocarcinomas and islet cell tumours. colorectal cancer, cervical cancer.
anal cancer, uterine or other reproductive tract , urinary tract cancer, such as of the
ureter or bladder. germ cell tumour such as a testicular germ cell tumour or ovarian germ cell
tumour, ovarian cancer, such as an ovarian epithelial cancer, oma of unknOWn primary,
hilman immunodeficiency associated malignancy, such as Kaposi's sarcoma, lymphoma.
leukemia, malignant ma, sarcoma, endocrine , such as of the thyroid gland.
mesothelioma or other pleural or peritoneal tumour, neuroendocrine tumour or carcinoid
By “co-administration” is meant that the stabilised particulate material and the cellular
toxin are administered as separate entities in their own right. In other words, at the time of
administration the stabilised particulate material and the cellular toxin are not covalently or
chemically coupled to each other.
Co-administration of the stabilised particulate al and the cellular toxin in the
context of the present invention includes both simultaneous and sequential administratiOn.
Simultaneous administration includes where the ised ulate material and the eeiiular
toxin are present in the same formulation or in two different formulations,_but each are
nevertheless administered at substantially the same time. In the case of sequential
administrationpa multi-step procedure is used where the stabilised particulate material is
administered in one step and the cellular toxin is administered at a different time in a separate
step. The cellular toxin may be administered prior to administration of the stabilised
particulate material. The time difference between administration of the stabilised ulate
al and the ar toxin in sequential administration can vary. but will generally range
from about 1 minute to about 4 days, for example from about l minute to about 2 hours. or
item about 1 minute to about 24 hours, or from about 1 minute to about l2 hours, or from
about 1 minute to about 6 hours, or from about I minute to about 3 hours, or from about 1
minute to about i hour.
In a sequential administration, the stabilised particulate material will generally be
stered prior to the cellular toxin.
The particulate material and the cellular toxin may be administered by the same or
different routes.
Without ng the present invention to any one theory or mode of action, once the
particulate material has penetrated the tumour, effective ation of the administered
celluiar toxin is aiso. achieved.
it will be appreciated that it is well within the skills of the person in the art, and in light
of the teaching provided herein, to select and design an administration protocol for the
elements herein described.
In a further aspect there is provided a method of treating a solid tumour in a subject,
said method comprising:
(a) administering to said subject an effective amount of particulate. material and for a time
and under conditions sufficient to facilitate distribution of said particulate material to
said tumour wherein:
(i) said particulate material is administered in the form of a dispersion in a liquid
carrier, the particulate material being maintained in the dispersed state by a
stabiliser; and
(ii) said stabiliser comprising an ing portion that (a) anchors the stabiliser to
the particulate material, and (b) is different from the remainder of the stabiliser;
W0 42669
(b) administering to
to said subject an effective amount of a ar toxin subsequently
administration of said particulate material;
and wherein said particulate material and toxin penetrate said solid tumour.
Where the stabiliser is a steric iser comprising a steric stabilising polymeric
is ent
segment and an anchoring n. wherein the steric stabilising polymeric segment
from the anchoring portion, the method of treating a solid tumour in a subject comprises:
(a) stering to said subject an effective amount of particulate material and for a time
and under conditions sufficient to facilitate distribution of said particulate material to
said tumour wherein:
(i) said particulate material is administered in the form of a sion in a liquid
carrier, the particulate al being maintained in the dispersed state by a
steric iser; and
(ii) said steric stabiliser comprising a steric stabilising polymeric segment and an
anchoring portion, wherein the steric stabilising polymeric segment is different
[5 from the anchoring portion, and wherein the anchoring portion anchors the
stabiliser to the particulate material; and
(b) administering to said subject an effective amount ofa cellular toxin subsequently to
administration of said particulate al;
and wherein said particulate material and toxin ate said solid tumour.
In yet another aspect there is provided a method of treating a solid tumour in a subject,
said method comprising co-administering to said subject an ive amount of particulate
material and a cytostatic or cytocidal agent for~a time and under conditions sufficient to
facilitate distribution of said particulate material and toxin to said tumour, wherein:
(i) said particulate material is administered in the form of a dispersion'in a liquid carrier,
the particulate al being maintained in the sed state by a stabiliser; and
(ii) said stabiliser comprising an anchoring portion that (a) anchors the stabiliser to the
particulate material, and (b) is different from the remainder of the stabiliser;
and wherein said particulate material and said cytostatic or cytocidal agent penetrate said solid
tumour.
Where the stabiliser is a steric stabiliser comprising a steric stabilising polymeric
segment and an anchoring n, wherein the steric stabilising polymeric segment is different
from the anchoring portion, the method of treating a solid tumour in a subject ses co—
administering to said subject an effective amount of particulate material and a cytostatic or
2012/000414
cytocidal agent for a time and under conditions sufficient to tate bution of said
particulate material and toxin to said tumour, n:
(i) said particulatemateriai is administered in the form of a dispersion in a liquid carrier,
the particulate material being maintained in'the dispersed state by a steric stabiliser;
(ii) said steric stabiliser comprising a sterie stabilising polymeric segment and an
anchoring portion, wherein the steric stabilising polymeric segment is different from
the ing portion, and wherein the anchoring portion anchors the stabiliser to the
particulate material;
and wherein said particulate al and said cytostatic or cytocidai agent penetrate said solid
tumour.
Examples of cytotoxic agents include, but are not iimited to, Actinomycin D,
Adriamycin, Arsenic Trioxide, Asparaginase, Bleomycin, Busulfan. sar,
latinum Carmustine, Chiorambucil, Cisplatin, Corticosteroids, Colieheamicin,
Cyclophosphamide, Daunorubicin, Docetaxel. Doxombicin, Epirubicin‘ Etoposide.
Fludarabine, Fluorouracii, Gemcitabina, Gemcitabine, Gemzar, Hydroxyurea, ldarubicin,
lfosfamide. lrinotecan, Lomustinei lan, Mercaptomurine, Methotrexate. Mitomycin,
Mitoxantrone, Oxaliplatin, Paciitaxei, Platinol, Platinex, Proearbizines Raltitrexeel. Rixin,
Steroids, Streptozocin, Taxol, re, Thioguanine. Thiotepa, Tomudex, Topotecan,
‘ Treosulfan, Trihydrate, Vinblastine, Vincristine, Vindesine, Vinorelbina, Vinorelbine,
duanomycin, dactinomysin, esorubisin, mafosfamide, ne arabinoside, bis«
chloroethylnitrosurea, Mitomycin C, mithramycin, prednisomz, hydroxyprogesterone,
testosterone. fen, dacarbazine, hexamethylmeiamine, pentamethylmelamine, amsacrine,
chlorambudil, methylcyclohcxylnitrosurea, nitrogen mustards, Cyclophosphamide, 6-
mercaptopurine, 6-thioguanine, cytarabine. S-azacytidine. deoxyco-i‘ormycin‘ 4-
,hydroxyperoxycyclophosphoramide, S-fluorouracil , S-fluorodeoxyuridine (S-FUdR),
colchicine, trimetrexate, oside, diethylstilbestrol.
Reference to “cellular toxin" should also be understood to extend to any other
molecule which is perhaps not traditionally regarded as a cytotoxic agent but heless falls
3O within the scope of the present definition on the basis that it induces cellular damage, for
example DNA damage, such as nucleophosmin or agents which induce cellular damage as part
of a synergistic process with another agent. Examples include tic dies, prodrugs,
CHK [/2 inhibitor (such as CBP-SOI or AZD7762), histone deacetyiase inhibitor (such as
W0 2012/142669
-[3_
mimetic (such as
vorinostat), tumour necrosis factor d apoptosis inducing ligand or BH3
ABT737), small molecule inhibitors such as the tyrosine kinase inhibitors imatinib mesylate
c‘D), gefitinib (lressaQ) and erlotinib (Tarceva®), and the monoclonal antibodies (mAb)
such as mab (Mabthera®) and trastuzumab (Herceptin®).
in yet another embodiment, combination treatments may include, for example.
gemcitabine together with a CHK1/2 inhibitor or irinotecam together with a CHK l/2 inhibitor.
The particulate al and/or the stabiliser may be d to a ligand to effectfmore
specific targeting to a . This will not necessarily be applicable in every situation but, to
the extent that an appropriate target molecule exists for a given tumour, this may provide
additional useful Specificity.
According to such an embodiment, there is provided a method of treating a solid
tumour in a subject, said method comprising co-administcring to said subject an effective
amount of particulate material and a ar toxin for a time and under conditions ent to
facilitate distribution of said particulate material and toxin to said tumour, wherein:
(i) said particulate material is administered in the form of a dispersion in a liquid carrier,
the particulate material being maintained in the diSpersed state by a stabiliser; and
(ii) said iser comprising an anchoring portion that (a) anchors the stabiliser to the
particulate material, and (b) is different from the remainder of the stabiliser;
wherein the particulate material and/or the stabiliser is linked, bound or otherwise associated
with a ligand directed to a tumour le and wherein said' particulate material and toxin
penetrate said solid tumour.
Where the stabiliser is a steric stabiliser comprising a steric stabilising polymeric
segment and an anchoring portion, wherein the steric stabilising polymeric segment is different
from the anchoring portion, there is also provided a method of treating a solid tumour in a
t, said method comprising co-administering to said t an effective amount of
particulate material and a cellular toxin for a time and under conditions sufficient to facilitate
distribution of said particulate material and toxin to said tumour, wherein:
(i) said particulate al is administered in the form of a dispersion in a liquid carrier,
the particulate material being maintained in the dispersed state by a steric stabiliser;
and
(ii) said steric stabiliser comprising a steric ising ric segment and an
anchoring portion, wherein the steric stabilising polymeric segment is different from
W0 2012/142669
the stabiliser to the
the anchoring portion, and wherein the anchoring portion anchors
particulate material;
wherein the particulate material and/or the steric stabiliser is linked, bound or otherwise
material
associated with a ligand directed to a tumour molecule and wherein said particulate
and toxin penetrate said solid tumour.
in yet another aspect, there isprovided the use of particulate material and a cellular
wherein:
toxin in the manufacture of a medicament for the treatment of a solid tumour
(i) said particulate material is in the form of a dispersionin a liquid carrier, the particulate
al being maintained in the dispersed state by a stabiliser; and
(ii) said stabiliser comprising an anchoring portion that (a) anchors the stabiliser to the
particulate al, and (b) is different from the remainder of the stabiliser;
and wherein said particulate al and toxin penetrate said solid tumour.
Where the stabiliser is a steric stabiliser comprising a steric stabilising polymeric
t and an anchoring portion, wherein the steric stabilising polymeric segment is
' from the anchoring n, there is provided the use of particulate material and a ar toxin
in the manufacture of a medicament for the ent of a solid tumour wherein:
(i) said particulate material is in the form of a dispersion in a liquid Icarrier, the particulate
material being maintained in the dispersed state by a steric iser; and
(ii) said steric stabiliscr comprising a steric ising polymeric segment and an
anchoring portion, wherein the steric stabilising polymeric segment is different from
the ing portion, and wherein the anchoring portion anchors the stabiliser to the
particulate material;
and wherein said particulate material and toxin penetrate said solid tumour.
Further s and/or embodiments of the invention are discussed in more detail
below.
2012/000414
BRIEF DESCRIPTION OF THE DRAWINGS
Figure l: Sterically stabilised nanoparticles are able to penetrate into spheroids.
TEM images of the accumulation of NPZ particles in Spheroids. Arrows indicate areas of
tticle accumulation. Boxed regiort is enlarged and shown in the image on right. Scale
bars as indicated.
Figure 2: Nanoparticles can influence the diffusion of fluorescent active nds.
Co-administration of the fluorescent active compounds a) doxorubicin and b) mitoxantrone
with nanoparticles from examples 2, 3, and 5. Single confocal images of fluorescent drug
diffusion into DLD-l spheroids. Scale bar 200 pm.
ED Figure 3: The majority of rticles tested did not affect cellular outgrowth from
spheroids. Plot of normalised cellular outgrowth as described in example 29 of the
nanoparticles listed in examples 1, 2. 4, 8. 9, 12. l3. l5, l6, and IS. Error bars represent
rd error.
Figure 4: Composition of the ,nan0particle core does not influence nanoparticle
'15 iveness, Plot of normalised cellular outgrowth as described in example 29 of the
nanoparticles from examples 2, 4, 6. 7, 9, 10, ll. [2, l3, I4. 16, 17, and 18. co-administered
with doxorubicin. The untreated control Spheroids had a normalised outgrowth value of 331%
+/- 23. Error bars represent standard error.
Figure 5: Nanoparticle size does not correlate with nanoparticle effectiveness. Plot of -
normalised cellular outgrowth as described in e 29'of the nanoparticles listed in
examples 1,2, 4, 7, 9, 10, 11, 12, 13, i4, 16, 17, and 18 co-administered with doxorubicin. The
untreated control spheroids had a ised outgrowth value of 331% +/- 23. Error bars
represent standard error.
Figure 6: Nanopartieles stabilised with 5-10% amine onalised polymer increase the
effectiveness of ‘doxorubicin. Plot of normalised cellular wth as described in example
29 of the nanoparticles listed in examples 2, 3. 4. 5, 20. 21, 22, and 24. co-administered with
doxorubicin. The untreated control spheroids had a ised outgrowth value of 33l% +/-
23. Error bars represent standard error.
Figure 7: Effectiveness of co—administration of NPs with 5% amine functionalised
stabiliser end group coatings with different cores and doxorubicin compared to
doxoru bicin alone. Plot of normalised cellular outgrowth as describedm example 29 of the
nanoparticles listed in examples 2, 8, 9, and 12 co-administered with doxorubicin. The
W0 2012/142669
~16-
bars
untreated control ids had +/- 23. Error
a ised outgrowth value of 331%
represent standard error.
Figure 8: The efl'ect of'the active compounds when co-administered with nanoparticles on
the viability of spheroids made from two different cancer cell lines. Plot of normalised
cellular outgrowth as described in example 29 of the nanoparticles listed in examples 2, 3, 4,
and 5 co-administered with active compounds (Table 2). The untreated DLD-l control
ids had a normalised outgrowth value of 331% +/- 23. The untreated PA-l control
spheroids had a normalised outgrowth value of 294% +/- 2i. Error bars represent standard
error.
Figure 9: Effect of delayed administration of active compound compared to co-
administration of active compound and nanoparticlcs. Plot of normalised cellular
outgrowth as described in example 29 of the nanoparticles listed in examples 2, 3, 4, and 5
DLD—l spheroids were either co-administered nanoparticles and active nd (light grey
bars) or administered nanoparticles, then 24 hours later treated with active compound (dark
grey bars). The untreated DLD-l l spheroids had a normalised outgrowth value of
331% +/- 23. Error bars represent standard error.
Figure 10: Effect of delayed administration of active cOmpound compared to co-
administration of active compound and nanOparticles. Plot of normalised cellular
outgrowth as described in example 29 of the rticles listed in examples 2, 3, 4, and 5.
PA-l spheroids were either co-administered nanoparticles and active compound (light grey
bars) or administered nanoparticles, then 24 hours later treated with active compound (dark
grey bars).The untreated PA-l control spheroids had a ised outgrowth value of 294%
+/- 21. Error bars represent standard error.
Figure 11: The most effective inistered nanoparticle and active combinations for
DLD-l and PA-l cells. Plot of ised cellular outgrowth as described in example 29 of
the nanoparticles listed in es 2. 5. I4, 20, 2]. and 22, co-administered with active
compounds in DLD-l ids (A) and PA-l Spheroids (B). Error bars represent standard
error.
Figure 12: The covadministration of NPZ but not NP19 or NPZS with doxorubicin
3‘0 promotes doxorubicin ion througimut the spheroid. Cenfocal images of doxorubicin
diffusion in spheroids treated with 1 pM Doxorubicin and the nanoparticlesas indicated. Scale
bar 200 pm.
Figure 13 shows a schematic illustration of stabilised ulate material that may be used in
-17.
accordance with the present invention.
Figure 14 shows a schematic illustration of stabilised ulate material that may be used in
accordance with the present invention.
Figure 15 shows a schematic illustration showing the hydrodynamic volume of a stabilised
particulate material.
DETAILED PTION OF THE INVENTION
The present invention is predicated, in part, on the determination that particulate
material which is ined in a sed state by a certain type of stabiliscr can achieve a
deeper and more effective penetration into a solid tumour than has been previously achievable
using particle technology. The nature of the penetration effected by these particulate materials
has achieved both a cantly wider cellular distribution, within the tumour, of the tbxin co-
administered with the particulate material and, further, more effective ion of cellular
toxicity: Since reticuloendothelial clearance from the sites of tumours is significantly less
effective than in normal tissue. the method of the invention enables not only more effective
tumour ation but, further, the delivery of lower concentrations of cellulai toxins which
are enabled to localise, and thereby concentrate. at tumour sites. This reduces the side effects
which would be apparent in the context of conventidnal systemic chemotherapy where such
treatment would be delivered at the highest dose which can be tolerated by the patient and,
further, often in the context of multiple repeated rounds over a period of months. This
development now provides a realistic means of moving away from the treatment of primary
tumours and metastatic disease via the rgeted, systemic delivery of chemotherapy.
Reference to a “solid tumour” herein should be understood as a reference to an
encapsulated or unencapsulated mass or other form of growth or cellular aggregate which
comprises neoplastic cells. nce to a “neoplastic cell" should be understood as a
reference to a cell exhibiting abnormal growth. The term “growth" should be understood in its
st sense and includes nce to proliferation. The phrase “abnormal growth” in this
context is intended as a reference to cell growth which, relative to normal cell growth. exhibits-
one or more of an se in the rate of cell divisiori, an increase in the number of cell
ons, a decrease in the length of the period of cell division, an increase in the frequency of
periods of cell on or uncontrolled proliferation and evasion of apoptosis. Without
limiting the present ion in any way, the common medical meaning of the term
“ne0piasia” refers to new cell growth that results as a loss‘of responsiveness to normal growth
-18.
controls, e.g. to neoplastic cell growth. Neoplasias include “tumours" which may be either
benign, pro-malignant or malignant. The term “neoplasm” should be understood as a reference
form of growth or
to a lesion, tumour or other encapsulated or psulated mass or other
cellular aggregate which comprises neoplastic cells.
The term “neoplasm”, in the t of the present invention should be understood to
include reference to all types of cancerous growths or oncogenic processes, metastatic tissues
or state
or malignantly transformed cells, tissues or organs irrespective of histOpathologic type
of invasiveness.
The term “carcinoma” is recognised by those skilled in the an and refers to
malignancies of epithelial or endocrine tissues including respiratory system carcinomas,
gastrointestinal system carcinomas, urinary system omas, testicular carcinomas,
breast carcinomas, prostate carcinomas, endocrine system carcinomas and melanomas.
Exemplary carcinomas include those g from tissue of the breast. The term also es
carcinosarcomas, e.g. which include malignant tumours composed of carcinomatous and
sarcomatous s. An “adenocarcinoma” refers to a carcinoma derived from glandular
tissue or in which the tumour cells form recognisable lar structures.
The neoplastic cells comprising the neoplasm may be any cell type, derived from any
tissue, such as an epithelial‘or non-epithelial cell. Examples of neoplasms and stic Cells
encompassed by the t invention include, but are not limited to central nervous system
tumours, retinoblastoma, neuroblastoma and other paediatric tumours, head and neck cancers
(e.g. squamous cell cancers), breast and prostate cancers, lung cancer (both small and non-
small cell lung ), kidney cancers (cg. renal cell adenocarcinoma), oesophagogastric
cancers, hepatocellular carcinoma, pancreaticobiliary neoplasias (e.g. adenocarcinomas and
islet cell tumours). ctal cancer, cervical and anal cancers, uterine and other reproductive
tract cancers, urinary tract cancers (e.g. of ureter and bladder), germ cell tumours (e.g.
testicular germ cell tumours or ovarian germ cell tumours), ovarian cancer (e.g. n
epithelial cancers), carcinomas of n primary, human immunodeficiency associated
malignancies (cg. 's sarcoma), mas, malignant melanomas, sarcomas,
endocrine tumours (e.g. of thyroid gland), mesothelioma and other pleural or peritoneal
tumours, neuroendocrine s and carcinoid tumours.
Preferably, the present invention is directed to the treatment of a malignant neoplastic
condition and even more preferably a metastatic neoplastic condition. it would‘be appreciated
that although the method of the invention can be applied to the treatment of any neoplasm, it is
particularly useful in terms of the treatment of metastasised neoplasms. Without limiting the
present invention to any one theory or mode of action, non-metastasised primary tumours are
treatable either by the method of the invention or by conventional treatment regimes such as
surgical on of the tumour or radiotherapy. r, tumours which have metastasised
are not curable by either of these conventional treatment regimes due to the often extensive
spread and growth of metastatic nodules. Accordingly, such conditions are currently only
treatable by the administration of systemic chemotherapy, this treatment regime often g
severe side effects for limited curative potential. Still further, even in the context of primary
tumours which appear not to have asised, chemotherapy is still often recommended
following surgery and radiation in case metastatictsmead has occurred but is not yet detectable.
This is a particularly common practice in the context of cancers which are traditionally
regarded as aggressive, such as breast and colon s. ‘The method of sent invention
now provides an alternative to the application of aggressive systemic chemotherapy treatment
regimes. Since the systemic administration of the cytotoxic agent of the present invention is
able to be delivered in a more localised fashion to tumours and is more effectively metabolised
by the neoplastic cells, the occurrence of side effects can be minimised via the administration
of lower doses of the cellular toxin.
in one embodiment, said solid tumour is benign.
in r embodiment, said solid tumour is ant.
Preferably, said malignant solid tumour is a metastatic malignant soiid tumour.
Reference to “metastatic” should be understood as a nce to a tumour which either has
undergone metastatisation or may have undergone metastatisation.
in one embodiment, said malignant solid tumour is a central s system tumour,
biastoma, neurobiastoma, paediatric tumour. head and neck cancer such as squamous cell
cancer, breast and prostate , lung cancer, kidney cancers, such as renal cell
areinoma, oesophagogastric , hepatocellular oma, pancreaticobiliary
neOplasia, such as adenocarcinomas and islet cell tumours, colorectal cancer, cervical cancer,
anal cancer, uterine or other reproductive tract cancer, urinary tract cancer, such as of the
ureter or bladder, germ cell tumour such as a testicuiar germ cell tumour or ovarian germ cell
, ovarian cancer, such as an ovarian epithelial cancer, carcinoma of unknown primary
human immunodeficiency associated malignancy, such as Kaposi's sarcoma, lymphoma.
leukemia, malignant melanoma, sarcoma, endocrine , such as of the thyroid gland,
mesothelioma or other pleural or peritoneal tumour, neuroendocrine tumour or carcinoid
-20..
tumour.
As detailed hereinbefore, the method of the present invention is based on the co—
administration of a cellular toxin with stabilised particulate material. Previous attempts at
using particulate material, such as nanoparticles. to target tumours for either diagnostic or
therapeutic purposes have been extensive but, in the context of therapeutics, of minimal
success} With diagnostics, relatively shallow penetration of the particles into the tumour has
been sufficient to achieve the objective of visualisin'g the tumour. However, in terms of the
delivery of a therapeutic agent, such shallow penetration has not been sufficient to effectively
deliver the agent hout the tumour, in particular to the or of the tumour. In on
to therapeutics, specifically, conjugation of particles to a wide variety of different materials has
so far failed to live up to the promise of achieving effective tumour penetration, this being an
essential prerequisite for a eutic to have any chance of effectiveness.
icant effort has also been made to take advantage of the enhanced permeability
and retention (EPR) effect of tumours as a means to develop an effective therapeutic. Without
limiting the present invention to any one theory or mode of action, this is a well described
phenomenon based on the notion that certain sizes of molecules, typically liposomes or
macromolecular drugs, tend to preferentially accumulate in tumour . The general
explanation for this phenomenon is that, in order for tumour cells to grow y, they must
stimulate the production of blood vessels. VEGF and other growth factors are involved in
cancer angiogenesis. Tumour cell aggregates of sizes as small as I50~200um become
dependent on blood supply carried by culature for their nutritional and oxygen supply.
These newly formed tumour vessels are usually abnormal in form and architecture. They
comprise poorly-aligned defective endothelial cells with wide fenestrations. lacking a smooth
muscle layer, or innervation with a wider lumen, and impaired functional receptors for
angiotcnsin Il. rmore,tumour tissues y'lack effective tic ge. All
these .factors will lead to abnormal molecular and fluid transport dynamics, especially for
macromolecular drugs. Accordingly, it has been t that one way to achieve selective
drug targeting to solid tumours is to exploit these abnormalities of tumour vasculature in terms
of active and selective ry of anticancer drugs to tumour tissues, notably defihing the EPR
effect of macromolecular drugs in solid tumours. Due to their large molecular size, nanosized
macromolecular anticancer drugs administered intravenously escape renal clearance. Often
they cannot penetrate the tight endothelial junctions of normal blood vessels. but they can
W0 2012/142669 2012/000414
extravasate in tumour vasculature and become trapped in the tumour vicinity. Nevertheless.
the EPR effect has not been efficiently or successfully harnessed.
Various nanOparticles have been designed which are directed to achieving efficient
cellular endocytosis. However, even if this is able, the issue of tissue penetration is still
a separate one which, to date, has not been successfully overcome. The general notion of the
in the literature but,
use of a nanOparticle as a vector for delivery of a drug is widely sed
in the e of achieving deep tumour penetration, is of limited value.
Even where effective tumour distribution of a drug is achieved (by whatever means) a
further problem has been the fact that neoplastic cells within solid tumours can exhibit a
slowed metabolism. This means that even if a cytotoxic drug penetrates to these cells, if it is
not effectively metaboliscd it will have a limited impact on the viability of the .
t limiting the present invention to any one theory or mode of action. the method
of the present invention is thought to e its therapeutic es by both deep penetration
of the tumour by the particulate material, which y enables simultaneous or sequential
IS penetration by a cellular toxin, and enabling ive metabolism of the toxin so as to achieve
cell death. Still without limiting the present ion in any way, it is thought that this may be
due to the particulate material defined herein, by virtue of their design, acting to upregulate
cellular metabolism which has become slowed ordonnant.
The cellular toxin of the present invention should be understood as any proteinaceous
or non—proteinaceous molecule or group of molecules which will either retard cell growth or
induce cell death, for example either by directly killing the cell or else delivering a signal
which induces apoptosis. That is, the agent may be either cytostatic or cytocidal, it would be
appreciated by the persowof skill in the an that the method of the present invention can be
designed to deliver one cellular toxin or multiple cellular toxins (Le. a “cocktail” of drugs).
The decision in relation to how best to proceed can be made by the person of skill in the art as
a matter cf routine procedure. For example, depending on the tumour type, certain'specil‘tc
drugs or combinations of drugs are regarded as particularly desirable to use. it would be
appreciated that the body of knowledge in relation to the teristics and use of cytotoxic
agents is ive and the person of skill in the art could design an administration protocol to
meet the parameters of the t invention as a matter of routine ure.
Reference to “cellular toxin” herein should therefore be understood as a reference to
any agent which acts to damage or destroy cells. Without limiting the present invention to any
one theory or mode of action, many such agents function via the induction of apoptotic
W0 2012/142669
is not the only mechanism by which such agents function and‘it is processes. r, this
vable that the subject damage or cell death may be d by some other mechanism.
Examples of cytotoxic agents include, but are not limited to, Actinomycin D. Adriamycin,
Arsenic Trioxide, Asparaginase, Bleomycin, Busulfan, Camptosar, Carboplatinum.
Carmustine, Chlorambucil. Cisplatin, Corticosteroids, eamicin, Cyclophosphamide,
Daunorubicin, Docetaxcl, Doxorubicin, Epirubicin, Etoposide, Fludarabine, Fluorouracil.
Gemcitabina, Gemcitabine, Gemzar, Hydroxyurea. ldarubicin, lfosfamide, lrinotecan,
Lomustine, Melphalan, Mercaptomurine, Methotrexate, cin, Mitoxantrone.
Oxaliplatin, Paclitaxel, ol, Platinex, Procarbizine. Raltitrexeel. Rixin. Steroids,
Streptozocin, Taxol, Taxotere, Thioguanine, Thiotepa, x, Topotecan, Treosulfan,
Trihydrate, stine, Vincristine, Vindesine, Vinorelbina, lbine, ycin,
dactinomysin, esorubisin, mafosfamide, cytosine arabinoside, bis~chloroethyInitrosurea,
Mitomycin C, mithramycin, prednisone. hydroxyprogesterone, testosterone, tamoxifen,
dacarbazine, hexamethylmelamine, pentamethylmelaminc, amsacrine, chlorambudil,
methylcyclohexylnitrosurea, nitrogen ds, Cyclophosphamide, 6-mercaptopurine. 6-
thioguanine, bine, S—azacytidine, deoxyco-formycin, 4~
hydroxyperoxycyclophosphoramide, S-fluorouracil (S-FU), S-fluorodcoxyuridine (S-FUdR),
colchicine, trimetrexate, teni-poside, diethylstilbestrol.
However, reference to “cellular toxin” should also be understood to extend to any other
2O molecule which is perhaps not traditionally regarded as a cytotoxic agent but nevertheless falls
within the SCOpe of the present definition on the basis that it induces cellular damage, for
example DNA damage, such as nucleophosmin or agents which induce cellular damage as part
of a synergistic process with another agent. Examples include catalytic antibodies, gs.
CHKl/Z inhibitor (such as CBP-SOI or AZD7762). e deacetylase inhibitor (such as
vorinostat), tumour necrosis factor related apoptosis inducing ligand or BH3 mimetic (such as
ABT737), small molecule inhibitors such as the tyrosine kinase inhibitors-imatinib mesylate
(GlivecQ), gefitinib (lressa‘m) and erlotinib va®), and the monoclonal antibodies (mAb)
such as rituximab era®) and trastuzumab (Herceptinw).
in yet another embodiment, combination treatments may include, for example,
gemcitabine together with a CHKI/Z inhibitor or irinotecam er with a CHKI/2 inhibitor.
in a still further embodiment, the cellular toxin may be a molecule which functions as
an RNA interference mechanism. Without limiting the present invention to any One theory or
~23-
mode of action “RNA interference" broadly describes a methanism of gene ing which
based on degrading or otherwise ting the translation of mRNA in a sequence specific
manner. in terms of the application of this technology to selectively knocking down gene
expression, exogenous double stranded RNA (dsRNA) specific to a gene sought to be d
down can be introduced into the ellular nment. Once the dsRNA enters the cell, it
is cleaved by an RNaselllelike enzyme‘ Dicer, into double stranded small interfering RNAs
(siRNAs) 2i-23 nucleotides in length that contain 2 nucleotide overhangs on the 3' ends. in an
ATP dependent step. the siRNAs become integrated into a'multi-subunit protein complex
known as the RNAi induced silencing complex (RISC), which guides the siRNAs to the target
RNA sequence. The siRNA unwinds and the antisense strand s bound to RISC and
directs degradation of the complementary target mRNA ce by a combination of endo-
and exonucleases. However, whereas the RNAi mechanism was ally identified in the
context of its role as a microbial defence mechanism in higher eukaryotes, it is also known that
RNAi based gene expression knockdown can also function as a mechanism to regulate
endogenous gene sion. Specifically, microRNA (miRNA) is a form of endogenous
single-stranded RNA which is typically 20-25 nucleotides and is nously transcribed
from DNA, but not translated into protein. The DNA sequence that codes for an miRNA gene
generally es the miRNA sequence and an approximate e cempiement. When this
DNA sequence is transcribed into a single—stranded RNA molecule. the miRNA sequence and
its reverse-complement base pair to form a double stranded RNA hairpin l00p, this forming the
primary miRNA ure (pri-miRNA). A nuclear enzyme cleaves the base of the hairpin to
form RNA. The pre-miRNA molecule‘is then actively transported out ”of the nucleus
into the cytoplasm where the Dicer enzyme cuts20-25 nucleotides from the base of the hairpin
to release the mature miRNA.
Although both of the RNA interference mechanisms detailed above effectively achieve
the same outcome, being selective gene expression knockdowm RNAi based on the use of
exogenously administered dsRNA generally results in mRNA degradation while RNAi based
on the s of miRNAs generally s in translational repression by a mechanism which
does not involve mRNA degradation. The RNA interference which is contemplated in the
context of the present invention should be understood to encompass reference to both of these
RNAi gene knockdowri mechanisms. The induction of this miRNA based knockdown
mechanism could be achieved by administering. in accordance with the method of the
invention, exogenous RNA oligonucleotides of the same sequence as an miRNA. pre-miRNA
should understood that these exogenOus RNA
or RNA molecules. r, it be
oligonucleotides may lead to either mRNA degradation (analogous to that observed with the
introduction of an exogenous siRNA pepulation) or mRNA translateral repression, this being
akin to the mechanism by which the endogenous miRNA molecules function. in terms of the
objective of the. present invention, the occurrence of either gene knockdown mechanism is
able.
The RNA interference mechanism herein discussed is effected via the use of an RNA
oligonucleotide which can induce an RNA interference mechanism. Reference to an “RNA
oligonucleotide" should thereforebe understood as a reference to an RNA nucleic acid
l0 molecule which is double stranded or single stranded and is capable of either effecting the
induction of an RNA interference mechanism directed to knocking down the expression of a
in this regard,
gene targeted or downregulating or preventing the onset of such a mechanism.
the t oligonucleotide may be capable of directly modulating an RNA interference
mechanism or it may require further sing, such as is teristic of hairpin double
stranded RNA which requires on of the hairpin region, longer double stranded RNA
les which require cleavage by dicer or sor molecules such as RNA which
similarly require cleavage: The subject oligonucleotide may be double stranded (as is typical
in the context of effecting RNA interference) or single stranded (as may be the case if one is
seeking only to produce a RNA oligouucleotide suitable for binding to an endogenously
sed gene). Examples of RNA oligonucieotides suitable for. use in the context of the
present invention include, but are not limited to: _
(i) long double stranded RNA (dsRNA) — these are generally produced as a result of the
hybridisation of a sense RNA strand and an antisense RNA strand which are each
separately transcribed by their own vector. Such double stranded molecules are not
characterised by a hairpin loop. These molecules are required to be cleaved by an
enzyme such as Dicer in order to generate short interfering RNA (siRNA) duplexes.
This cleavage event preferably occurs in the cell in which the dsRNA is transcribed.
(ii) hairpin double stranded RNA (hairpin dsRNA) — these molecules exhibit a 00p
configuration and are generally the result of the transcription of a construct with
inverted repeat sequences which are separated by a nucleotide spacer region, such as an
intron. These molecules are generally of longer RNA molecules which require both
'the hairpin loop to be cleaved off and the resultant linear double stranded molecules to
be cleaved by Dicer in order to te siRNA. This type of molecule has the
-25..
advantage of being expressible by a single .
(iii) short interfering RNA (siRNA) — these can be synthetically generated or, recombinantly
expressed by the promoter based expression of a vector comprising tandem sense and
antisense strands each terised by its .own promoter and a 4-5 thymidine
transcription termination site. This enables the generation of 2 te transcripts
which subsequently anneal. These transcripts are generally of the order of 20-25
nucleotides in length. Accordingly, these molecules require no further ge to
enable their functionality in the RNAi pathway.
(iv) short hairpin RNA (shRNA) - these les are also known as “small hairpin RNA”
and are similar in length to the siRNA molecules but with the exception that they are
expressed from a vector comprising inverted repeat sequences of the 20-25 nucleotide
RNA molecule, the inverted repeats being separated by a nucleotide spacer.
Subsequently to cleavage of the hairpin (loop) region. there is generated a functional
siRNA molecule.
(V) micro RNA/small temporal RNA (miRNA/srRNA) —‘miRNA and stRNA are generally
understood to ent naturally ing endogenously expressed molecules.
' Accordingly, although the design and administration of a molecule intended to mimic
the activity of a miRNA will take the form of a synthetically generated or
rccombinantly expressed siRNA' molecule, the method of the t invention
nevertheless extends to the design and expression of oligonucleotides intended to
mimic miRNA, pri-miRNA or pre-miRNA molecules by virtue of exhibiting
essentially identical RNA sequences and overall structure. Such recombinantly
generated les may be referred to as either miRNAs or siRNAs.
(vi) miRNAs which mediate l development (stNAs). the stress se (srRNAs)
or cell cycle (ccRNAs).
(vii)? RNA oligonucleotides designed to ise and prevent the functioning of
endogenously sed miRNA or stRNA or exogenously introduced siRNA. It
would be appreciated that these molecules are not designed to invoke the RNA
interference mechanism but, rather, prevent the upregulation of this pathway by the
miRNA and/or siRNA molecules which are present in the intracellular environment,
In terms oftheir effect on the miRNA to which they hybridise, this is reflective of
more classical antisense inhibition.
it .will be appreciated that the person of skill in the art can determine the most suitable
W0 2012/142669
—26—
RNA oligonucleotide for use in any given situation. For example, although it is preferable that
the subject oligonucleotide exhibits l00% complementarity to its target nucleic acid molecule.
nevertheless exhibit some degree of mismatch to the extent that
the oiigonucleotide may
hybridisation sufficient to induce an RNA interference response in a ce specific manner
is enabled. Accordingly, it is red that the oligonucleotide of the present invention
ses least 70% complementarity, more preferably at least 90%
at sequence
complementarity and even more preferably, 95%, 96%, 97%, 98% 99% or 100% sequence
complementarity.
In another example pertaining to the design of oligonucleotides suitable for use in the
to determine the
present invention, it is within the skill of the person of skill in the art
particular structure and length of the subject oligonucleotide, for example r it takes the
form of dsRNA, hairpin dsRNA, siRNA, shRNA, miRNA, pre-miRNA. pri-miRNA etc. For
example, it is generally tood that oop RNA structures, such as hairpin dsRNA and
shRNA, are more efficient in terms of achieving gene knockdown than, for e, double
stranded DNA which is generated utilising two constructs separately coding the sense and
antisense RNA strands. Still further, the nature and length of the intervening spacer region can
impact on the functionality of a given stem-loop RNA molecule. In yet still another example,
the choice of long dsRNA, which requires cleavage by an enzyme such as Dicer. or short
dsRNA (such as siRNA or shRNA) can be relevant ifthere is a risk that in the context ofthe
particular cellular environment an interferon response could be generated. this being a more
icant risk where long dsRNA is used than where short dsRNA molecules are utilised. in
still yet another example, r a single stranded or double stranded nucleic acid molecule is
required to be used will also depend on the functional outcome which is sought. For example.
to the extent that one is targeting an endogenously expressed miRNA with an antisense
molecule. it would generally be appropriate to design a single ed RNA oligonucleotide
suitable for specifically hybridising to the t miRNA. However, to the extent that it is
sought to induce RNA interference, a double stranded siRNA molecule is required. This may
be designed as a long dsRNA molecule which undergoes further cleavage or an siRNA. Still
further, the final
present invention. is preferably ed to result in the generation of a
effector RNA oligonucleotide (i.e. a siRNA or miRNA le) which is preferably leSS than
nucleotides in length, more ably l5~25 nucleotides in length and most preferably l9,
,21, 22 or 23 nucleotides in length.
Stabilised particulate material in accordance with the invention can advantageously be
2012/000414
maintained in a diSpersed state at low concentrations. The ability for the particulate material to
‘in a dispersed state in a diverse array of liquid carriers (including body fluids) at
relatively low tration, coupled with the ability to tailor the design of the stabiliser on a
molecular level (e.g. its composition and molecular weight), may, without wishing to be
limited by theory; play a role in enabling the particulate material to achieve deep penetration of
solid tumours.
As used herein, the expression “particulate material" is intended to embrace al -
that is capable of being dispersed throughout the liquid carrier and that presents a surface to
which the stabiliser maybe associated.
The particulate material will generally be of a size that is less than about 500 nm. less
than about 350 nm, less than about 250 nm. less than about l00 nm, less than about 50 nm, less
than about 25 nm or less than about 15 nm.
In one embodiment, said particulate material is about: 2, 4, 6, 8, IO, 20, 30, 40, 50, 60.
70, 80, 90, too, 110, no, I30, 140, ISO, 160, I70. 180, l90, 200. 2l0. 220, 230. 240, 250.
260, 270, 280, 290, or 300 nm.
By having an ability to be dispersed throughout the liquid carrier, it will be appreciated
that the particulate material will be sufficiently insoluble in the liquid carrier so as to enable
the dispersion to have effective application.
The particulate material may be in the form of primary particles, or in the form or an
aggregation of primary particles.
For avoidance of any doubt, reference herein to the “size” of the ulate material is
intended to denote an average size (at least about 50 number %) of the particles based on the
largest dimension of ‘a given particle. The size of the particulate material per se is ined
herein by Transmission Electron Microscopy (TEM).
For avoidance of any doubt. when the particulate material is. in the form of an
aggregation of primary particles, reference to the size of such material is intended to be a
reference to the largest ion of the aggregate not the primary particles that form the
aggregate.
‘ Apart from having medicinal utility in the context of the present application, there is no
ular limitation on composition of the ulate al. The particulate material may
have an organic composition or an inorganic composition or a combination thereof. The
ulate material may be inorganic, organic or a combination thereof.
Examples of ulate material include one or more of a metal, a metal alloy, a metal
salt, oxide, an inorganic oxide, a radioactive isotope, a polymer
a metal complex, a metal
particle, and/or combinations thereof.
and salts,
More specific examples of particulate materials include gold, silver, boron,
chromium oxide,
complexes or oxides thereof, calcium carbonate, barium sulphate, iron oxide,
cobalt oxide, manganese oxide, n oxide, iron oxyhydroxide, chromium oxyhydroxide,
cobalt oxyhydroxidc, ese oxyhydroxide, chromium dioxide, other transition metal
oxides, polymers such as polystyrene, p0|y(methyl methacrylate) and poly(butadiene).
In some embodiments of the invention, it is red that the particulate material is
magnetic. ic particulate al that may be used in accordance with the invention
will generally be of a size of less than about 350nm. Those skilled in the art will appreciate
that the composition and/or size of the particles can influence their magnetic properties. The
magnetic particulate al will generally t ferromagnetic, ferrimagnetic or
superparamagnetic preperties.
The specific size of the magnetic particulate material used will generally be dictated by
the intended application of the compositions. For some applications, it may be desirable for
the magnetic particulate material to be of a size of less than about 300 nm, for example less
than about 100 nm, or less than about 50 nm.
There is no particular tion on the type of magnetic particulate material that may
be used in ance with the invention. Examples of suitable magnetic materials include,
but are not limited to, iron. nickel, chromium, cobalt, oxides thereof or mixtures of any of
these. Preferred iron oxide magnetic particulate materials include Hon oxide (i.e. y-FezOg,
also known as maghemite) and magnetite (Fe304).
in that is
some applications, it may be desirable to use magnetic material
superparamagnetic (i.e. uperparamagnetic panicles). As used herein, the term
"superparamagnetic” is intended to mean magnetic particles that do not have the following
properties; (i) coercivity, (ii) remanence, or (iii) a hysteresis loop when the rate of change of an
applied magnetic field is quasi static.
The ic material is preferably selected from ferrites of general a
03 where M is a bivalent metal such as Fe, Co, Ni, Mn, Be, Mg, Ca, Ba, Sr, Cu, Zn, Pt
or mixtures thereof, or oplumbite type oxides of the general formula MO.6Fe203 where
M is a large bivalent ion, ic iron, cobalt or nickel. Additionally, they could be particles
of pure Fe, Ni, Cr or C0 or oxides of these. ‘Altematively they could be mixtures of any of
these.
I’CT/AU2012/000414
In one embodiment, the magnetic particulate material is or comprises iron oxide such
less than 50 nm,
as magnetite (F6304) or maghemite (y-Fe203) with a particle size preferably
for example between 2 and 40 nm.
Particulate material used in accordance with the invention may conveniently be
prepared using ques knowrt in the art.
In accordance with the invention, the particulate al is maintained in the dispersed
state by a stabiliser. By being “maintained" in this context is meant that in the absence of the
stabiliser the particulate material would otherwise late or settle out from the liquid_
carrier as sediment. in other words, the stabiliser functions to retain the particulate material in
the dispersed state.
The alate al is in the form of a dispersion within a liquid carrier, the
particulate material being maintained in the dispersed state by a stabiliser. By “stabiliser" is
meant an agent that associates with the particulate material and assists with preventing it from
flocculating or otherwise becoming non-dispersed within the liquid carrier.
The stabiliser used in accordance with the inventiOn comprises an anchoring portion
that (a) anchors the stabiliser to the particulate material, and (b) is different from the remainder
of the iser.
By an “anchoring portiOn" is meant a moiety such as an atom or group of covalently
d atoms that functions to anchor the stabiliser to the particulate material.
By an anchoring portion that “anchors” the stabiliser to the particulate material is
meant it is the anchoring portion per se that directly tethers or binds the stabiliser to the
particulate material.
The ing portion therefore binds the stabiliser to the ulate material.
There is no particular limitation on the way in which the stabiliser is anchored to the
particulate material. For example, it may be covalently coupled to the particulate material.
and/or secured to the ulate material through electrostatic forces, hydrogen bonding, ionic
charge, van der Waals forces, or any combination thereof.
The stabiliser functions to prevent the particulate material from flocculating or
otherwise becoming nonvdispersed (i.e. aggregated) within the liquid carrier h known
mechaniSms such as steric repulsion, osteric repulsion and/or electrostatic repulsion.
Without wishing to be limited by theory, use of a stabiliser in accordance with the
invention is believed to facilitate (i) transport of the ulate al in vivo to the site of
the solid tumour, and/or (ii) penetration the particulate material throughout the solid tumour,
W0 2012/142669
and/or (iii) uptake by subpopulations of cells within the tumour that would not otherwise
accumulate effective doses of the cellular toxin.
One or more stabiliser can be uSed in accordance with the present invention.
By the anchoring portion being “different” to the remainder of the stabiliser is meant
that the anchoring portion has a different ure or molecular composition to the rest of
stabiliser. In other Words, the stabiliser will have a ising portion (i.e. the portion that
functions as a stabilising moiety) and an anchoring portion (i.e. the portion that functions to
secure or bind the stabiliser to the particulate material). The stabilising portion and the
anchoring portion are ent.
By providing the stabiliser with different ural features that give rise to the
stabilising and anchoring functions, it has been found that practical effect of both functions can
be enhanced. Without wishing to be limited by theory, a strong'association between the
ulate al and‘the stabiliser (provided by the anchoring portion). in ation with
dedicated ising moiety is believed to enable the particulate material to be maintained in a
dispersed state throughout a diverse array of liquid carriers at very low trations. Such
properties make the particulate material well suited to being maintained in a dispersed statc
post stration within body fluids.
Those skilled in the art will appreciate that stabilisers with a unique anchoring portion
can function differently to stabilisers without such a unique anchoring portion, For example, a
stabiliser such as polyethylene glycol (PEG) can adsorb to the surface of a particulate material
and on as a stabiliser. In that case, any part(s) of the PEG chain, which does not have an
anchoring portion that is different from the remainder of the stabiliser, will adsorb in a random
fashion giving rise to a non-uniform surface stabilising layer.
In contrast, by ing a stabiliser with a stabilising portion and different anchoring
n arrangement a more controlled .and uniform surface stabilising layer can
advantageously be formed. For e the presence of the unique anchoring portion can
promote on the surface of the particulate material a brush stabilising layer. where the
anchoring n is d to the surface of the particulate material and the remainder ofthe
stabiliser (he. the stabilising. portion) s out from the surface of the particulate material
into the liquid carrier akin to the bristles extending from the surface of a brush (hence the name
"brush" stabilising layer). As ahcase in point, the PEG stabiliser mentioned above might be
functionalised with one or more carboxylic acid groups at the end of the PEG chain to provide
for an anchoring portion. The acid functionalised anchoring portion, which is different from
W0 2012/142669
the remainder of the stabiliser, can then Secure or bind the PEG chain to the particulate
material and allow it to extend freely into the carrier liquid.
Suitable stabilisers may be nonionic, anionic, cationic, or zwitterionic.
in one embodiment, the particulate material is maintained in the dispersed state by a
steric stabiliser, wherein the steric stabiliser comprises a steric ising polymeric segment
and an anchoring portion, wherein the steric stabilising polymeric segment is different from the
anchoring portion, and wherein the anchoring n binds the stabiliser to the ulate
material.
In a similar manner to that outlined above, steric stabilising ric segment
functions to stabilise the particulate material within the liquid carrier, and the anchoring
portion functions to secure the stabiliser to the particulate material. By providing the stabiliser
with different Structural features that give rise to the steric stabilising and anchoring functions.
it has been found that practical effect of both functions can be enhanced.
Examples of le stabilisers include, but are not limited to, those having a
polymeric stabilising segment.
The stabilising segment will be soluble in the liquid carrier.
in one embodiment, the polymeric ising segment cemprises polymer selected
from polyacrylamide, polyethylene oxide, polyhydroxyethylacrylate, poly N:
isopropylacrylamide, polydirnethylaminoethyImethacrylate, polyvinyl p‘yrrolidOne and
copolymers thereof.
In another embodiment, the anchoring portion comprises one or more ylic acid
groups, One or more phosphate , one or more phosphonate groups. one or more
phosphinate groups, one or more thiol groups. one or more thiocarbonylthio groups. one or
more sulfonic acid groups, one or more ethoxysilyl , and combinations f.
ln one embodiment, the anchoring portion is an anchoring polymeric segment and at
least one of the steric stabilising and anchoring polymeric ts comprise polymerised
residue of one or more ethylenically unsaturated monomers. Employing at least one such
ric t is believed to enhance the stabilising pr0perties of the steric stabiliser.
in one embodiment. the anchoring portion is an anchoring polymeric t and at
least one of the steric stabilising and anchoring polymeric segments'is derived from one or
more ethylenicaily unsaturated monomers that have been “polymerised by a living
polymerisation technique. Employing at least one such polymeric'segment is ed to
e the stabilising properties of the steric stabiliser.
By being a “steric” 'stabiliser is meant that stabilisation of the particulate material
throughout the liquid carrier occurs as a result of steric repulsion forces. Having said this, the
steric stabiliser may present electrostatic repulsion forces that also assist with stabilisation
the particulate material. The steric stabilising function of the iser'used in aCcordancc
with the ion therefore plays an important role in enabling the particulate material to be
maintained in a dispersed state hout a diverse array of liquid carriers, including body
fluids.
In one embodiment, the stabiliser used in accordance with the invention comprises an
ionisabie functional group that does not form part of the anchoring portion and presents within
the carrier liquid a cationic or c charge. Stabiliser comprising such ble functional
group(s) (e.g. amine or carboxylic acid) may be present in an amount ranging from about 2
wt% to about 50 wt%, or about 5 wt % to about 40 wt%, relative to the total wt % of stabiliser
used. The use of this type of stabiliser provides for electrosteric isation. The ce of
such stabiliser has surprisingly been found to e penetration of the particulate material.
in one embodiment, the stabiliser comprises a steric ising polymeric segment
having a terminal (i.e. at the end of the r segment or chain) functional group. The
onal group may be an ionisable functional group, such as one that can provide for a
cation (e.g. amine) or an anion (carboxylic acid). In one embodiment the ionisable
functional group provides for a cation.
In a further embodiment, the stabiliser comprises a steric stabilising polymeric segment
having a terminal functional group selected from an amine a carboxylic acid and an alcohol
The amount of stabiliser used relative to the particulate material will vary depending
on the nature of the particulate material, particularly its size. For example, lg of Snm
particulate material will require more stabiliser than i g of 1 micron particulate material due to
its increased surface area. Those skilled in the art will be able to determine the ed
amount of stabiliser for a given. particulate material.
For avoidance of any doubt, reference herein to specific features of the “stabiliscr” is
intended to embrace all forms of stabilisers contemplated for use in ance with the
invention (i.e. where the stabiliser comprises an anchoring portion that is different form the
remainder of the stabiliser, or where the stabiliser is a steric stabiliser sing a steric
stabilising polymeric segment and an anchoring portion. Wherein the steric stabilising
polymeric segment is different from the anchoring portion).
in one embodiment, the stabiliser used in ance with the invention comprises a
polymeric structure. There is no particular limitation on the molecular weight of the stabiliser,
and this feature of the stabiliser may be dictated in part on the mode by which the sion
to be administered to a subject. The stabiliser may. for example. have a number average
molecular weight of up to about 160,000, or up to about 150,000, or up to about 100,000, or up
to about 50,000.
in one embodiment. the isers used in ance with the present invention will
haVe a relatively low number average molecular weight compared with Stabilisers
conventionally used to stabilise particulate material.
in some embodiments of the invention, it may be preferable that the number average
molecular weight of the stabiliser is less than about 30,000, or less than about 20,000, or less
than abOut , or even less than about 5,000. The number average molecular weight of‘ the
stabiliser may also range from about 1,000 to about 3,000.
Stabilisers used in accordance with the invention having. a quite low number average
IS molecular weight (e.g. less than about 5,000, preferably in the range of from about 1,000 to
about 3000) have been found to be particularly effective at stabilising particulate al in
viva.
lar weight values referred to herein are number average molecular weight
values (Mn). if appropriate, the molecular weight is to be determined using gel permeation
chromatography (GPC). GPC can be performed using polystyrene standards for hydrophobic
polymers and polyethylene oxide standards for hilic polymers.
Those skilled in the art will appreciate that determination of the lar weight for a
block copolymer may e additional procedures. For example, it may useful to determine
the molecular weight of the first block before the second block is added. If a block is less than
about 3000 molecular weight this can be determined by ospray mass spectroscopy
(EMS). For higher molecular weigh , GPC can be employed using polystyrene
standards for hydrophobic blocks and polyethylene oxide standards for hydrophilic blocks.
Determining the molecular weight of an overall block copolymer will typically depend
on the length of the two blocks and their solubility characteristics. The molecular weight of
low molecular weight block copolymers can be determined by EMS as mentioned above. For
higher molecular weight block copolymers for which suitable solvents and standards can be
found, GPC may be used. For example, if both blocks are hydrophobic and soluble in, for
example, tetrahydrofuran (THF), GPC can be carried out against polystyrene standards; if both
WO 42669
blocks are hydrophilic and soluble in, for example, THF, it may be useful to use hylene
oxide standards, rather than polystyrene standards. However, it may be that the blocks of a
block copolymer are too dissimilar to allow for a common dissolving solvent; poly acrylamide-
b-polystyrene is an example of such a block copoiymer.
in that case, it will generally be
necessary to first block and then grow the second block and prepare and characterise the
calculate the molecular weight of the second block on the basis of the degree of conversion
monomer to polymer.
Stabilisers used in accordance with the invention can advantageously exhibit highly
efficient stabilising properties in abilisation ofthe particulate material can be achieved at
both low and high concentrations of the particulate material within a liquid carrier. The
stabilisers can also provide for stable dispersions of the particulate material throughout a
diverse array of liquid carriers, such as those having a high ionic strength (e.g. 0.!5 M NaCl
solution, and even as high as in a saturated NaCl solution at room ature), and also over a
wide pH range. Such properties make the dispersions particularly suitable for in vivo
IS applications.
Without wishing to be d by theory, the highly efficient stabilising properties that
can be provided by the stabilisers are believed to stem at least in part from isers
comprising an ing portion that is separate to and different from the stabilising portion
and securely s the stabiliser to the particulate material.
By nce the stabiliser being “anchored" to the particulate material, or wherein the
anchoring portion “anchors" the stabiliser to the particulate material, is meant that the stabiliser
is securely attached to the paniculate material within a liquid carrier and‘can remain so
attached in the absence of free stabiliser in the liquid carrier, where the liquid r has a high
ionic strength (cg. saturated aqueous sodium chloride solution), and/or where the liquid carrier
has a low ionic strength (cg. pure water).
Anchoring of the stabiliser to the particulate material may be achieved as a result of the
anchoring portion being (I) covalently coupled to the particulate al, and/or (2) secured to
the particulate material through electrostatic forces, hydrogen bonding, ionic charge, Van 'der
Waals forces, or any combination thereof.
As a result of the isers being ed to the particular material, the ulate
material can be maintained in a diSpersed state within the liquid carrier despite it being present
at low or high concentration and/or the liquid carrier having low or high ionic strength.
Accordingly, a dispersion of the particulate material in a liquid carrier in accordance
-35.
under conditions that
with the ion can be advantageously stable (Le. does not flocculate)
conventionallystabilised particulate material would be le (i.e. would flocculate).
Those skilled in the art will appreciate that stabilisers that are not covalently bound to
particulate al generally stabilise and in particulate material in a dispersed state by
ng in from
a state of equilibrium of being adsorbed to and ed the particulate
material. Accordingly, where a stabiiiser is present at a relatively low concentration in a given
liquid carrier. the equilibrium is generally shifted in favour of the stabiliser'being desorbed
from the ulate material, which in turnresults in flocculation of the particulate material.
Where anchoring occurs by the stabiliser being covalently coupled to the particulate
material, there can of course be no desorption of the stabiliser. Where anchoring occurs by
other means, the stabilisers used in accordance with the present invention are nevertheless
securely attached to the particulate material and therefore undergo iittle if no desorption from
the particulate material even when present at low concentration within the liquid carrier. In
other words, when present at low concentration» within the liquid carrier the equilibrium of
adsorbed stabilisers used in accordance with the invention is strongly in favour of the stabiliser
being adsorbed to the particulate material, which in turn facilitates the particulate material
being maintained in a diSpersed state.
A convenient test to confirm the anchoring characteristic of 'stabilisers used in
ance with the invention, which in turn may also reflect their ability to maintain the
particulate material in the required dispersed state, can be performed by diluting the steric
stabilised particulate material to l% solids using a suitable liquid carrier (typically water),
centrifuging this solution so that the solids form a plug, and then ng the supernatant
liquid to isolate the solid plug. The solid plug is then combined with a suitable liquid carrier
(typically water) without adding more iser so as to again form l% solids. Sodium
de is then added to the resulting solution to yield 10% by‘weight sodium chloride. lithe
particulate material can be redispersed in this final solution and remains diSpersed for at least 1
hour, the steric stabilisers are regarded as being ed to the particulate material.
By “steric stabilising polymeric segment" is meant a segment or region of the steric
stabiliser that is polymeric (Le. formed by the polymerisation of at least one type of monomer)
and that provides for the steric stabilising function of the steric stabiliser. For convenience, the
steric stabilising polymeric segment may hereinafter be referred to as polymeric segment A‘
As mentioned. the steric stabilising polymeric segment ons to stabilise the
particulate al throughout the liquid r by providing, steric repulsion forces.
By being polymeric, it will be appreciated that the steric stabilising segment ses
polymerised monomer residues. Thus, the segment will comprise polymerised monomer
residues that give rise to the required steric stabilising properties. The polymerised menomer
residues that make up the steric ising polymeric t may be the same or different.
The steric stabilising polymeric segment may be substituted with a moiety (eg. an
optional substituent as herein defined), or contain a polymerised monomer residue, that gives
rise to electrostatic ising properties.
To provide the desired stabilising effect, the stabilising portion will be soluble in at
least the liquid carrier. The solubility ofa given stabilising portion in a given liquid carrier can
readily be determined by simply preparing the stabilising portion in isolation and conducting a
suitable solubility test in the chosen liquid carrier.
Similarly. to provide the d steric stabilising effect, the steric stabilising polymeric
segment will be soluble in at least the liquid carrier. The solubility ofa given steric stabilising
polymeric segment in a given liquid carrier can readily be determined by simply preparing the
polymeric segment in isolation and conducting a le solubility test in the chosen liquid
carrier.
The stabiliser as a whole; may or may not be soluble in the given carrier liquid. but will
nonethelesspresent a stabilising n that is soluble.
Those skilled in the art will have an understanding of polymeric materials that may be
ed as the steric ising polymeric segment, as to the monomers that may be
polymerised to form such polymers. For example, suitable polymeric als include, but
are not limited to, polyacrylamide, polyethylene oxide, polyhydroxyethylacrylate. poly N-
'isopropylacrylamide, polydimethylaminoethylmethacrylate, polyvinyl pyrrolid0nc and
copolymers thereof. Thus, suitable monomers that may be used to form the stabilising
polymeric segment' include, but are not limited to, acrylamide, ethylene oxide,
hydroxyethylacrylater ropylacryiamide, dimethylaminoethylmethacrylate, vinyl
idone and combinations f.
The particular steric stabilising polymeric segment used as part of the steric stabiliser
will of course depend upon the nature of the liquid carrier. For example. if an aquedus liquid
carrier is used, the steric stabilising polymeric segment should be e in the aqueous
media. Those skilled in the art will be able to select an appropriate steric stabilising ric
segment for the chosen liquid carrier.
By being able to select a specific steric stabilising polymeric segment independent of
W0 42669
portion, steric stabilisers used in accordance with the ion
the anchoring can
advantageously be tailor designed to suit a particular liquid carrier and thereby maximise the
stabilising properties of the steric stabiliser.
There is no particular limitation concerning the polymerisation that technique may be
used to prepare the steric stabilising polymeric t. Living polymerisation techniques
have been found particularly useful in that . Those skilled in the art will appreciate that ~
“living polymerisation" is a form of radical addition polymerisation whereby chain growth
that give rise to
pr0pagates with essentially no chain transfer and essentially no termination
dead polymer . By a “dead r chain” is meant one that can not undergo further
addition of monomers.
in a living polymerisation, typically all polymer chains are initiated at the start of the
polymerisation with minimal new chains being initiated in latter stages of the polymerisation.
After this initiation process, all the polymer chains in effect grow at the same rate.
Characteristics and properties of a living polymerisation generally include (i) the molecular
weight of the polymer increases with conversion, (ii) there is a narrow distribution of polymer
chain lengths (i.e. they are of similar molecular weight), and (iii) additional monomers can be
added to the polymer chain to create block co~polymer structures. Thus living polymerisation
enables excellent control over molecular weight, polymer chain architecture and polydispersity
of the resulting polymer that can not be achieved with non-living polymerisation s.
Suitable living polymerisation techniques may be selected from ionic polymerisation
and controlled radical polymerisation (CRP). Examples of CR? include, but are not limited to,
iniferter polymerisation, stable free radical mediated polymerisation (SFRP). atom transfer
radical polymerisation (ATRP), and reversible on fragmentation chain transfer (RAFT)
polymerisation.
The steric stabilising polymeric t may be formed by the polymerisation of one
type of monomer or a combination of two or more ent monomers. ingly. the
steric stabilising polymeric segment may be a homopolymeric segment or a copolymeric
segment.
Given that the stabilising polymeric segment forms only part of the steric iser,
rather than defining the steric stabilising polymeric t in terms of its number average
lar weight, it can instead be useful to make reference to the number of polymerised
monomeric units that collectively form the segment. Thus, although there is no particular
tion on the number of such units that collectively form the steric stabilising polymeric
segment. in some embodiments of the invention it may be desirable that the steric stabiliser has
in that case, it is preferable that the steric
a relatively low number average molecular weight.
stabilising polymeric t has less than about 100, more preferably less than about 50.
most preferably from about 10 to about 30 polymerised monomer e units that make up
the overall segment.
The steric stabilisers used in ance with the ion also comprise an anchoring
portion. The function of the anchoring portion has been mentioned. Provided that the
stabiliser can be suitably anchored to the particulate material and is different to the steric
stabiliser, there is no particular limitation concerning the form of the anchoring portion.
The anchoring portion will be covalently coupled to the steric stabilising segment. For
convenience. the anchoring portion may be represented as “B“. The steric stabilising
polymeric segment and the anchoring portion may be covalently coupled by any le
means. For example. the steric stabiliser may be described as or comprising the structure A-C‘-
B, where A represents the steric stabilising polymeric segment, B represents the anchoring
portion and C represents a coupling moiety. Alternatively, the steric ising polymeric
t and the anchoring portion may be directly covalently coupled and therefore the
‘stabiliser can be simplistically described as or comprising the structure AB. in that case, A
ents the steric ising polymeric segment and 8 represents the anchoring portion.
The Specific anchoring portion used will generally be dictated by the nature of the
particulate material to which it is to be anchored. Those skilled in the art will be able to select
an appropriate ing portion to bind with the surface of a given particulate material.
When selecting the steric stabilising segment and anchoring portion. it may be
desirable to consider the properties of these respective ents in the context of the
intended application of the sion. For example, one or both of the steric stabilising
segment and anchoring portion may be selected such that they are biodegradable and/or
biocompatible,
The anchoring n may be present as one or more moieties that form a 00valent
bond with the particulate material so as to covalently couple the stabiliser to the particulate
material. For example, the anchoring portion (in an anchored state). may be derived from a
thin! moiety (-SH) that ntly couples the stabiliser to the particulate material via a -S-
linkage. in other words, the stabiliser used comprises a thiol , but it will be ntly
coupled to the particle via a -S— linkage. Accordingly, reference to a stabiliser “used“ in
accordance with the invention is ed to be a reference to the form of the stabiliser prior to
W0 2012/142669 PCT/AU2012l0004l4
it being anchored to the particulate material.
The anchoring portion may be a polymeric t, or in other words an anchoring
will
ric segment. in this form, anchoring of the stabiliser to the particulate material
generally of covalent coupling rather by way of electrostatic
not be by way but forces,
hydrogen bonding, ionic charge, Van der Waals forces, or any combination thereof.
By an “anchoring polymeric segment" is meant a segment or region of the steric
stabiliser that is polymeric and that has an affinity toward the e of the particulate
material and functions to anchor Or bind the steric stabiliser to the particulate material. For
convenience, the anchoring polymeric t may also be represented as “B”.
.10 By being polymeric, it will be iated that the anchoring segment comprises
polymerised monomer residues. The segment will se polymerised monomer residues
that give rise to the ed anchoring to the particulate material. The polymerised monomer
residues that make up the anchoring polymeric segment may be the same or ent.
The anchoring polymeric segment can present multiple sites for binding interactions
with the particulate material and it is believed that this property enables the stabiliser to be‘
anchored ly to the ulate material despite not being covalently coupled thereto.
Generally, the anchoring polymeric segment will have at least two polymerised
r residues that each provides a site for binding with the particulate material, preferably
at least three, more preferably at least five, still more preferably at least seven, most preferably
at least ten of such polymerised monomer residues. Not all of the polymerised monomer
residues that make up the anchoring ric segment are necessarily required to give rise to
a binding interaction with the particulate material, but it is generally preferred that the majority
if not all of the polymerised monomer residues that make up the anchoring polymeric segment
do give rise to a binding interaction with the ulate material.
The anchoring ric t may therefore be described as having le sites
that collectively anchor the stabiliser to the particulate material. Even where a given binding
site only provides a relatively weak interaction with the particulate material, the presence of
les of such sites within the segment enables it as a whole to bind securely with the
particulate material.
The anchoring polymeric segment can also be substituted with a moiety (cg. an
optional substituent as herein defined) that may or may not give rise to a binding interaction
with the particulate material.
The Specific anchoring polymeric segment used will generally be dictated by the nature
of the particulate material to which it is to bind. _
When bing the interaction of the anchoring polymeric segment with the
particulate material, it can be convenient to refer to the hilic and hydrOphobic character
of the segment and the particuiate material. Thus, in l. suitable g interactions will
or hydrophobic
occur when the segment and the ulate material have similar hilic
character. For example, where the particulate material has a relatively hydrophilic surface (e.g.
its surface can be wetted with water), then good binding should be attained using an anchoring
ric segment that has hydrophilic character (e.g. in its ed form the segment would
be soluble in an aqueous medium).
Such an example might be realised where the particulate material is of a type that can
form a charge on its surface. in that case, it may be ble for the segment to se
polymerised residues of monomers that can also form a charge (e.g. residues of an ionisable
monomer) so as to promote ionic binding between the segment and the particulate al.
Promoting the formation of such charged species might be facilitated by adjusting the pH of
the liquid carrier in which the stabiliser and particulate material reside.
By the term “ionisable monomer” is meant that the monomer comprises a functional
group which can be ionised in solution to form .a cationic or anionic group.
Such functional
loss
groups will generally be capable of being ionised under acidic or basic conditions through
or acceptance of a proton. Generally, the ional groups are acid groups or basic groups
(Le. groups that can donate or accept a H atom, respectively). For example, a carbox‘ylic acid
onal group may form a carboxylate anion under basic conditions, and an amine
functional group may form a quaternary ammonium cation under acidic conditions. The
functional groups may also be capable of being ionised through an ion exchange process.
Examples of suitable ionisable monomers having acid groups include, but are not
limited to, methacrylic acid, acrylic acid, itaconic acid, ene carboxylic acids, p-styrene
suifonic acids, vinyl sulfonic acid, vinyl phosPhonic acid, ryloxyethyl ate, 2-
(methacryloyloxy) ethyl phOSphate, ethacrylic acid, alpha-chloroacrylic acid, crotonic acid,
fumaric acid, citraconic acid, mesaconic acid, and maleic acid. Examples of suitable ionisable
monomers which have basic groups include, but are not limited to, 2-(dimethyl amino) ethyl
and propyl acryiates and methacrylates, and the corresponding 3u(diethylamino) ethyl and
propyl acrylates and methacryiates.
Those skilled in the art will be able to select an appropriate anchoring polymeric
segment to bind with the surface of a given particulate material.
-4].
By being able to select a specific anchoring polymeric segment independent of the
steric stabilising polymeric segment, the steric stabilisers used in accordance with the
invention can advantageously be tailor designed to suit a particular particulate material and
thereby maximise the anchoring properties of the steric stabiliser. For example, it may be
desirable that the anchoring polymeric t comprise carboxylic acid, phosphinale,
phosphonate and/or phosphate functional groups. Where the particulate material to which
anchoring segment binds ses iron (e.g. magnetic iron oxide particulate material), it may
be desirable for the segment to comprise phosphinate, onate, and/or phosphate
functional groups. Such segments will lly be formed using monomers that comprise the
phosphorous onal groups.
Those skilled in the art will appreciate the variety of polymeric materials that may be
employed as the anchoring polymeric segment, as to the rs that may be polymerised to
form such polymers. For e, suitable polymeric materials include, but are not d to,
polyacrylic acid, thacrylic acid, polystyrene, polyitaconic acid, poly-p-styrene
carboxylic acids, poiy-p—styrene suifonic acids,~polyvinyl sulfonic acid, polyvinyl phosphonic
acid, poly monoacryloxyethyl phosphate. poly-Z-(methylacryloyloxy) ethyl phosphate,
polyethacryiic acid, poly-alpha-chloroacrylic acid, poiycrotonic acid,—~poiyfumaric acid,
polycitraconic acid, polymesaconic acid, poiymaleic' acid, poly-Z-(dimethyi amino) ethyl and
propyl acrylates and methacrylatcs, the corresponding poly(diethylamino) ethyl and propyi
tes and methacrylates, hydrophobic acryiate and methacrylate polymers,
methylaminoethyimethacrylate, and copolymers thereof. Thus, suitable monomers that
may be used to form the anchoring polymeric segment include. but are not limited to, acrylic
acid, methacrylic acid, itaconic acid, p-styrene ylic acids, ene sulfonic acids, vinyl
sulfonic acid, Ivinyl phosphonic acid, monoacryioxyethyl phosphate, 2-(methylacryloyloxy)
ethyl phOSphate, ethacrylic acid, alpha-chloroacrylic acid, crotonic acid, fumaric acid,
onic acid, mesaconic acid, maleic acid, 2-(dimethyl amino) ethyl and propyl tes
and methacrylates, the corresponding 3-(diethylamino) ethyl and prOpyl acrylates and
methacrylates, styrene, hydr0phobic acrylate and methacrylate monomers,
dimethylaminoethylmethacrylate, and combinations thereof. _
Living polymerisation techniques such as those herein described have been found
particularly useful in preparing the anchoring polymeric segment.
v.Where the anchoring portion is an anchoring polymeric segmentpat least one of the
steric stabilising and anchoring polymeric segments may be derived from one or more
ethylenically unsaturated monomers that have been polymerised by a living polymerisation
technique. Where only one of the segments is d in this manner, it will ably be the
anchoring polymeric t.
The anchoring polymeric segment may be formed by the polymerisation of one type of
monomer or a combination of two or more different monomers. Accordingly, the ing
polymeric segment may be a homopolymeric t or a copolymeric segment.
Given that the anchoring polymeric segment may form only part of the steric stabiliser,
rather than defining the anchoring polymeric segment in terms of its number average
molecular weight, it can instead be useful to make reference to the number of polymerised
monomeric units that collectively form the segment. Thus, although there is no particular
limitation on the number of such units that collectively form the anchoring polymeric segment.
in some embodiments of the invention it may be desirable that the steric stabiliser has a
relatively low number average lar weight. In that cases it is rable'that the
anchoring polymeric segment has-less than about IOO. more ably less than about 40, still
more preferably less than about 30, even more preferably from about 5 to about 25. most
preferably from about 5 to about 15 polymerised monomer residue units that make up the
overall segment.
When selecting the steric stabilising and anchoring ric segment, or the:
monomers that may be used to prepare them, it may be desirable to consider the properties of
the» respective polymeric segments in the context of the intended application of the dispersion.
For example, oneor both polymeric segment may be selected such that they are biodegradable
and/or patible.
Provided that the stabiliser ons as herein described there is no particular
limitation on how the ising polymeric segment and the anchoring polymeric segment are
to be spatially arranged.
I'I‘he steric stabilising polymeric segment and the anchoring polymeric segment may be
coupled to each other by any suitable means to form the steric stabiliser used in accordance
with invention. For example. the steric stabiliser may be described as or sing the
structure A-C-B, where A represents the steric stabilising polymeric segment, B represents the
anchoring polymeric segment and C represents a coupling moiety. Alternatively. the steric
stabilising polymeric segment and the anchoring polymeric t may be directly coupled
to each other via a covalent bond and therefore the stabiliser can be simplistically described as
or comprising an A-B block copolymer. In that case, A represents the steric stabilising
2012/000414
polymeric t and B ents the anchoring polymeric segment.
lt wiil be appreciated from the description above that each of A and B can
independently be (e.g. random, block, tapered, etc.). The
a homdpolymcr or a copolymer
stabiliser may comprise more than one'steric stabilising polymeric segment (A) and more than
one anchoring polymeric segment (B). For example, the stabiliser may be described as or
comprising an A-B-A block copolymer. In that case, each A represents the steric ising
polymeric segment, which may be the same or different, and B represents the anchoring
polymeric segment. The stabiliser might aiso be described as or comprising a B-A-B biock
copolymer, where each B represents the anchoring polymeric segment. which may be the same
or different. and A represents the steric stabilising polymeric segment that is of sufficient chain
length such that it forms a “loop" that extends into the liquid carrier and performs its
ising role.
The stabiliser may also have more complex structures such as star and comb polymer
structures. in that case, the anchoring polymeric Segment B might represent the main polymer
backbone of such structures, with multiple .steric stabilising ric segments A being
attached thereto.
The interaction of a steric stabiliser used in accordance with the invention (in the form
of an A-B block copoiymer structure) with particulate material in the liquid carrier might be
illustrated in the not to scale simplified schematic shown in Figure l3.
; with reference to Figure l3, the c stabiliser represented by an A-B block
copoiymer exhibits an affinity toward the surface of the particulate al (P) through the
anchoring polymeric segment (B). The anchoring polymeric segment (B) therefore secures the
steric stabiliser‘to the particulate material. The anchoring polymeric segment (B) provides
multiple sites for binding interactions between the segment and the particuiate material. The
steric stabilising polymeric segment (A), which is ent to t (B). is soluble in the
liquid carrier and functions to maintain the ulate material diSpersed hout the liquid
carrier. it will be appreciated that in practice the e of the particulate material will have
illustration in
many steric isers secured thereto, and that these haye been omitted from the
Figure l3 for clarity.
A similar illustration to that in Figure 13 is shown in Figure l4 where the steric
stabiliser used in accordance with the invention is in the form of an A-B-A block copoiymer.
At least one of the steric ising and anchoring polymeric segments may be derived
from one or more ethylenically unsaturated rs that have been p‘olymerised by a living
YCT/AU2012/000414
polymerisation technique such as ionic polymerisation, iniferter polymerisation, SFRP, ATRP,
and RAFT risation. Of these living polymerisation techniques. RAFT risation
is preferred.
The stabiliser used ing to the invention may be prepared and then used to
stabilise the particulate material. atively, a moiety may be anchored to the particulate
material and that moiety used to tate polymerisation of monomer so as to grow the
stabiliser out from the particulate al.
Those skilled in the art will appreciate that the stabiliser selected for use in accordance
with the invention may depend on the nature of the particulate material being stabilised and the
way in which it is to be administered to a subject. For example, if the particulate material is to
be administered intravenously and is required to remain in circulation for some time, the
stabiliser may need to be a steric stabiliser as herein described.
If the particulate material is to be administered orally and needs to remain stable in the
high acid conditions of the stomach, the stabiliser may also need to be a steric stabiliser as
herein described. for example a steric iser comprising poly acrylamlde.
By the particulate material being “dispersed throughout” a liquid carrier is meant that
the particulate material presents as a dESpersed phase throughout the liquid r which itself,
relative to the particulate material, presents as a continuous liquid medium or phase. ln other
words. the composition might be described as comprising a suspension or diSpersion of the
particulate material throughout the liquid r.
As used herein. the term “liquid” in the t of the liquid carrier is intended to mean
a vehicle in which the particulate material is dispersed throughout and which is in a liquid state
at least at the temperature of intended use in the methods of the invention. Typically, a liquid
carrier will be considered to be in a “liquid” state if, in the absence of astabiliser, particulate
material dispersed throughout the carrier can ate or settle out from the carrier to form
sediment. In other words, if the particulate material can move relatively freely in the e,
then it is considered “liquid”.
The liquid carrier may be made up of one or more different liquids. Suitable
pharmacologically acceptable liquid carriers are described in Martin, Remington's
Pharmaceutical Sciences, 18‘h Ed, Mack Publishing Co., Easton, PA, (1990). Generally, the
liquid carrier will be an s liquid carrier. Water or soluble saline solutions and aqueous
dextrose and glycerol solutions are preferably ed as liquid carriers. ularly for
injectable solutions.
W0 2012/142669
pharmacologically acceptable ves
The dispersion may comprise one or more
known to those in the art. For example. the liquid carrier may comprise one or more ves
and preservatives.
such as wetting agents, devfoaming agents, surfactants, buffers, electrolytes,
liquid carrier and any additive therein (if present) will in
The particular nature of the
Those d in the art will be
part depend upon the intended application of the composition.
able to select a le liquid carrier and additive (if present) for the intended application of
the dispersion.
It should also be understood that the particulate material and/or (steric) stabiliser may
also be coupled to a ligand to effect more specific targeting, to a tumour. This will not
necessarily be applicable in every situation but, to the extent that an appropriate target
molecule exists for a given tumour, this may provide additional useful specificity.
Although the general notion of targeted therapy is not new, to date the s of
targeted therapy has been limited by virtue of meeting the criteria which have been required of
a potential target le, these being:
(i) cell surface location
(ii) high cell surface molecule density
(iii) lack of internalisation of the molecule; and
(iv) lack of appreciable antigen shedding from the cell surface.
Limitations do exist in terms of the fication of such molecules, in particular
antigens which are also ideally tumour~specific. However, to the extent that such s are
known for a given situation, they may be usefully exploited.
To this end, reference to a “ligand" should be tood as a reference to any
molecule having specificity (not necessarily exclusive specificity, although this is preferable)
'and binding affinity for a tumour molecule. Examples of ligands include immunointeractive
2-5 molecules, peptidomimetic agents, lanthamide metals (which interact with RNA species),
enzymatic substrates (which interact with cell death-related enzymes) and putrescine (which
interacts with tissue lutaminase). In one embodiment, the ligand is an
immunointeractive molecule. Although a preferred immunointeractive molecule is an
immunoglobulin molecule, the present invention extends to other immunointeractive
molecules such as antibody nts, single chain antibodies. nized antibodies
including humanized antibodies and T-cell ated antigen-binding molecules (TABMS).
Most ably, the immunointeractive molecule is an antibody such as a polyCIOnal or
monoclonal antibody. It should be understood that the t ligand may be linked, bound or
cell.
otherwise associated to any other proteinaceous or non-proteinaceous molecule or
The ligand is “directed to" the tumour molecule. it should be understood that the
ligand may not necessarily exhibit complete ivity, although this is preferable. For
example, antibodies are known to sometimes crossreact with other antigens.
An nic
determinant or epitope includes that part of the molecule to which an immune response can
directed. The antigenic determinant or epitope may be a B-cell epitope or where riate a
T~cell receptor binding molecule.
The t invention may also be designed such that a ligand is dir’ected to one or
more tumour molecules. Accordingly. the present invention may be designed to administer
two or more ligands directed to different targets, for example as a means of increasing the time
of cellular toxin which is delivered to a population of neoplastic cells. It also provides a
convenient means of simultaneously delivering two different toxins.
Where used, the ligand may be ly bound to the particulate material or indirectly
bound to the particulate material by fonning part of the steric iser. For example. the
ligand may be bound to the steric stabiliser.
Those skilled in the art will appreciate that the dispersed ulate material used in
accordance with the invention will present a hydrodynamic diameter within the liquid carrier.
The hydrodynamic diameter is the distance or size that is d from the ulate material
per se and the steric stabilisers associated with the particulate material. This can be more
clearly explained with reference to Figure 15 where the particulate material per se (IO) is
dispersed within a carrier liquid (not shown) by (steric) stabilisers (20). The hydrodynamic
diameter (30) of the dispersed particulate material can therefore be seen to represent the
diameter afforded by a combination of the particulate material and the (steric) stabilisers.
Where the sed particulate al does not have a symmetrical shape, the hydrodynamic
er will be considered to be that of the largest hydrodynamic diameter presented by the
dispersed particulate material.
Without wishing to be limited by theory, it is believed that the hydrodynamic diameter
of the dispersed particulate material may also play a role in facilitating deep penetration ofthe
particulate material within s.
In one embodiment, the hydrodynamic diameter of the dispersed particulate al is
less than about 500 nm. is less than about 350 nm, less than about 250 nm, less than about 100
nm, less than about 50 nm, less than about 25 nm or less than about IS nm.
In a further embodiment, the hydrodynamic diameter of the dispersed particulate
W0 42669
material is about: 10, 20, 30, 40, 50, 60, 70, 80,90, IOO, 110, 120, 130, I40, 150,- 160, I70,
180, 190, 200, 210, 220, 230. 240, 2,50, 260, 270, 280, 290, or 300 nm.
For avoidance of any doubt, reference herein to the “the hydrodynamic diameter“ of
the dispersed particulate material is intended to denote an average diameter (at least about 50
number °/o) of the dispersed particulate material. The ynamic diameter of dispersed
particulate material is determined herein by Hydrodynamic Chromatography (HDC, PL-PSDA
(Polymer Laboratories».
Reference herein to a “subject” should be understood to encompass , primates,
livestock animals (e.g. sheep, pigs, cattle, horses, donkeys). laboratory test animals (eg. mice,
rabbits, rats. guinea pigs), companion animals (e.g. dogs, cats) and captive wild animais (cg.
foxes, kangaroos, deer). Preferably, the mammal is a human.
it should be tood that the term “treatment” does not necessarily imply that a
subject is treated until total recovery. Accordingly, treatment includes reducing the severity of
an existing condition, amelioration of the symptoms of a particular condition or ting or
' otherwise reducing the risk of developing a particular condition.
An “effective amount” means an amount necessary at least partly to attain the desired
response, or to delay the onset or t progression or halt altogether, the onset or progression
of a particular condition being treated. The amount varies depending upon the health and
physical'COndition of the individual to be treated, the taxonomic group of individual to be
d, the degree of tion desired. the formulation of the composition, the assessment of
the medical situation, and other relevant factors. It is expected that the amount will fall in a
relatively broad range that can be determined through routine trials.
In a related aSpect of the present invention, the subject oing treatment may be
any human or animal in need of therapeutic treatment. in this regard, reference herein to
“treatment" is to be considered in its broadest context. The term “treatment" does not
necessarily imply that a mammal is treated until total recovery. ingly, treatment
includes amelioration of the symptoms of a particular condition or preventing or otherwise
reducing the risk of developing a particular condition. "Treatment" may also reduce the
severity of an ng condition.
Administration of the ulate material and cellular toxin, in the form of
pharmaceutical compositions, may be performed by any convenient means. The
pharmaceutical c0mposition is plated to exhibit therapeutic ty when administered
in an amount which depends on the particular case. The variation depends, for example. on the
-43.
for use. A
human or animal and the particular agent, particulate material and texin ed
applicable. Dosage regimes may beadjusted to provide the
broad range of doses may be
optimum therapeutic response.
Routes of administratiOn include, but are not limited to, respiratorally, racheally,
nasopharyngeally, intravenously, intraperitoneally, subcutaneously, intracranially,
intradermally, intramuscularly, intraoccularly, intrathecally, intracereberally, intranasally,
infusion, orally, rectally, via lV drip patch and implant. The particle may also be administered
directly to the tumour.
The compositions in accordance with the invention comprise pharmacologically
acceptable particulate material dispersed throughout a pharmacologically'acceptable liquid
carrier. By “pharmacologically acceptable” is meant that the particulate material, liquid
r, or other constituent of‘the compositiOn (cg. the steric iser) is suitable for
stration to a subject in their own right. ln other words, administration of the particulate
material, liquid carrier or other tuent of the composition to a subject will not result in
unacceptable toxicity, including allergenic ses and disease states.
As a guide only, a person skilled in the art may consider “pharmacologically
acceptable" as an entity approved by a regulatory agency of a federal or state government or
listed in the US Pharmacopeia or other generally recognised pharmacopeia for use in animals,
and more particularly humans.
Having said this, those skilled in the art will appreciate that the suitability of a
ition for administration to a subject and whether or not a given particulate material or
liquid carrier Would be considered pharmacologically acceptable, will to some extent depend
upon the mode of administration selected. Thus. the mode of administration may need to be
considered when evaluating whether a given composition-is suitable for administration to a
subject or pharmacologically acceptable.
The ceutical forms are preferably suitable for injectable use and include sterile
sterile
aqueous solutions (where water soluble) or dispersions and powders for the
stable oraneous preparation of sterile injectable solutions or sion. It must be
under the conditions of manufacture and storage and must be preserved against the
3O contaminating action of microorganisms such as bacteria and fungi. The carrier can be a
solvent or dispersion medium ning, for example, water, ethanol, polyol (for example,
glycerol, ene glycol and liquid polyethylene glycol, and the like), suitable es
thereof, and vegetable oils: The proper fluidity can be ined, for example, by the use of a
W0 2012/142669
in case of
coating such as lecithin. by the maintenance of the ed particle size the
dispersion and by the use of actants. The preventions of the action of micrOOrganisms
for example, parabens,
can be brought about by variOus antibacterial and ngal agents,
chlorobutanol, , sorbic acid, thimerosal and the like. In many cascs, it will be preferable
to include isotonic agents, for example. sugars or sodium chloride. Prolonged absorption of
the injectable compositions can be brought about by the use in the compositions of agents
delaying absorption, for e, aluminum monostearate and gelatin.
Sterile injectable solutions are prepared by incorporating the active compounds in the
required amount in the appropriate solvent with various of the other ients enumerated
above, as required. followed by filtered sterilisation. Generally. dispersions are prepared by
incorporating the various ised active ingredient into a sterile vehicle which contains the
basic dispersion medium and the required other ingredients from those enumerated above. in
the case of sterile powders for the preparation of sterile able solutions, the preferred
methods of preparation are vacuum drying and the freeze-drying technique which yield a
l5 powder of the active ingredient plus any additional desired ingredient from previously sterile-
filtered solution thereof.
ln one embodiment, the stabilised particulate material and cellular toxin may be
formulated in a single formulation. In an alternative embodiment. said stabilised ulate
material and cellular toxin are formulated in two separate ations.
The present invention is further described by reference to the following non-limiting
examples.
EXAMPLE 1
Steric stabilization of iron oxide rticles in aqueous dispersion using
poly(monoacryloxyethyl phOSphate)w-block—poly(acrylamide)zu macro raft agent.
Part (a): Preparation ofdiluted aqueousferrofluid stable in acidic medium.
Magnetite nanopanicles were produced following the method of Massar’t ration
of aqueous magnetic liquids in alkaline and acidic media. [BEE Transactions on Magnetics,
l98i. MAG-”(2): p. 1247—1248). In a typicalreaction, 80 ml of 1M FeCl3.6H20 in 2M HCl
and 40 ml of 1M FeClel-le in 2M HCI were mixed in a 2 Litre beaker and the mixture
d to 1.2 Litre with MQ-water. 250 ml H (28% (w/w)) was then quickly added to
the beaker and the mixture vigorously stirred for 30 minutes. Upon adding NH4OH, the colour .
of the mixture immediately turned from orange to black suggesting the formation of magnetite.
2012/000414
.50-
Magnetite was then oxidized in acidic medium to maghemite by heating at 90°C with iron
reddish brown.
e for about an hour. The colour of the suspension changed from black to
then decanted, washed acetone and
Maghemite particles were magnetically with finally
about] .5
peptized in water yielding a stable dispersion (5 wt %). The pH of the sion was
— 2.
Part (b): Preparation of a potflmonoacryloxyethy! ate)[0-b!ack~p0/y(acrylamide)20
macro-RAFT agent using: 2-{I(dodecylsulfanyl)carbonorhioyllsulfanyl} succinic acid.
A solution of odecylsulfanyl)carbonothioyl]sulfanyl} succinic acid (0.8l g, 2.0
mmol), 4,4’-azobis(4~cyanovaleric acid) (0.09 g, 0.3 mmol), acrylamide (2.87 g, 40.3 mmol) in
dioxane (15 g) and water (i S g) was prepared in a 100 'mL round bottom flask, This was stirred
magnetically and sparged with nitrogen for 15 minutes. The flask was then heated at 70°C for
4 hrs. At the end of this period, monoacryloxyethyl phosphate (3.98 g. 20 mmol) and 4.4’~
azobis(4-cyanovaleric acid) , 0.3 mmol) were added to the flask. The mixture was
deoxygenated and heating was. continued at 80°C for a further 12 hours. The copolymer
solution had 23.6% solids. The copolymer solution was then diluted with MQ water to 0.7 wt%
and the pH ed to 5 using 0.IM NaOH.‘ .
Part (a): Preparation of sterically stabilized iron oxide nanoparticles from the aqueous
ferroflm‘d ple 1, part (a) and the macro~RAFT agent ofexample 1. part (b).
Nanoparticle dispersion prepared in example 1 part (a) (27 g) was d with MQ
water (200g) to yield a 2 wt% dispersion of the nanoparticles. The pH of this nanoparticle
sion was then raised to 5 using 0.1 M sodium hydroxide. The 2 wt% dispersion of the
iron oxide dispersion was then added to the macro—RAFT copolymer solutiOn from example l,
part (b) (100 g). The mixture was stirred vigorously with an overhead stirrer for 45minutes
before the pH was adjusted to pH 7 using sodium hydroxide solution. The mixture was then
left to stir vigorously for r 2 hours at room temperature. The nanoparticle dispersion was
then dialysed to remove salts, residual solvents, unwanted low molecular weight reaction side,
products and unbound polymer. Bigger particles in the dispersion were removed by
ultracentrifugation. The purified nanoparticlc sion was then distilled to increase the
solids loading in the aqueous ferrofluid dispersion to about 70 wt%. The resulting aqueous
ferrofluid was found to be stable in 60% ammonium nitrate solution.
EXAMPLE 2
Steric stabilization of iron oxide nanoparticles in aqueous dispersion using 95%
poly(monoacryloxyethyl ate)lO—block-poly(ethylene oxide)” macro raft agent and
W0 2012/142669
macro raft agent
% onoacryloxyethyl phosphate)I0-block-poly(acrylamide)25
monometftyl with 2-
Part ,(a): Estenfication of poly(ethy1ene glycol) ether
{[(butylsulfany!)carbonothioyllsuyanylfpropanoic acid
it. and
MethoxyPEG (Mn ~798) was warmed and stirred to liquefy and homogenize
bottom flask, and then
19.95 g (25.0 mmol) was then weighed into a 250 mL 3-necked round
d to solidify. utylsulfanyl)carbonothioyl]sulfanyl}propanoic acid (6.96 g, 29.3
mmol) and 4-dimethylaminopyridine (360 mg, 2.9 mmol) were added to the flask, a magnetic
stirbar was introduced, and the flask was purged with nitrogen. Dry dichloromethane (75 mL)
all dissolved. The flask was then
was added and the mixture was d until the solids had
' cooled in an ice bath and a Solution of N,N'-dicyclohexylcarbodiimide (6.03 g, 29.3 mmol)
dry dichloromethane (25 mL) was then added dropwise over 1 h. The reaction was d in
the-ice-bath for a further 10 min, then at room ature for 24 h. The resulting yellow
slurry was diluted with 1:1. hexane-ether (I00 mL) and filtered through a sintered glass funnel.
The filter residue was washed with further small portions of H -ether until it was
i5 white, and the combined filtrates were evaporated to give a cloudy and gritty dull orange oil.
The crude product was dissolve in dichloromethane (75 mL) and stirred with solid oxalic acid
(4 g) for l h. then diluted with hexane (70 mL) and allowed to settle, producing a flocculent
white precipitate. The mixture was filtered and evaporated. and the crude oil was dissolved in
2:1 hexane-dichloromethane (150 mL) and passed through a plug of alumina (40 g). Elution
with further 2:] hexane~dichloromethanc was continued until the eluate was colourless. The
combined eluates were dried with sodium te, filtered, and evaporated to give a clear pale
orange oil, 24.69 g, 97%.
Part (b): Preparation of a poly(ethylene oxide)! 7-block-poiy(monoacryloxyethy!
phosphate)10 macro-Rafi agent based on (he macro—RA FT ple 2 part (a).
A on of RAFT-PEG from example 2 part (a) (3.60 g, 3.5 mmol), 4,4’-azobis(4-
cyanovaleric acid) (0.20 g, 0.7 mmol), monoacryloxyethyl ate (689 g, 35 mmol) in
dioxane (45 g) and water (22.5 g) was prepared in a 250 mL round bottom flask. This was
stirred magnetically and sparged with nitrogen for IS minutes and the reaction was carried out
at 70°C for 12 hours. The copolymer solution had l5.l% solids. The copolymer solution was
then diluted with MQ water to 0.7 wt% and the pH adjusted to 5 using 0.1M NaOH.
Part (C): Preparation of a po(y(manoacryloxyethyl phasphatefl0-block-poly(acrylamide)20
‘ macro-RAFT agent using 2-{[(butylsulfanyI)carbonor}:ioyl/suVanyipr-opanoic acid.
acid (3.2 g, 13.6
A solution of 2-{[(butylsulfanyl)carbonothioyl]sulfanyl}propanoic
mmol), zobis(4—cyanovaleric acid) (0.19 g. 0.7 mmol), acrylamide (19.27 g, 271.1
round bottom flask. This
mmol) in dioxane (45 g) and water (22.5 g) was prepared in a 250 mL
for 15 minutes. The flask was then placed
was d magnetically and d with nitrogen
in’ a 70°C for 4 hrs. The homopolymer solution had 32.0% solids. 15g of the obtained
lymer solution, monoacryloxyethyl phosphate (4.50 g, 22.9 mmol) and 4,4’-azobis(4-
cyanovaleric acid) (0.043, 0.2 mmol) were added to a lOOmL round bottom flask. The mixture
flask stirred in a 70°C oil bath
was deoxygenated by en sparging for 15 minute and the
for 12 hours. The copolymer solution, which contained 40.4% , was then diluted with
MQ water to 1.2 wt%. The pH of the diluted copolymer solution was adjusted to S with 0.1M
NaOH.
Parr (d): Preparation of ally stabilized iron oxide nanopartr‘cles from the aqueous
ferrofluld of example 1 part (a) and a 95:5 blend of the macro-RAFT agent of example 2
part (b)aml lhe macro-RAFT agent ofexample 2 part (c).
A nanopartlcle dispersion prepared ing to example 1, part (a) was d with
MQ water to yield a 2 Wt% dispersion of the nanoparticles. The pH of this prepared
nanoparticle dispersion was then raised to S. A blend of macro-RAFT which consist of 50 g of‘
a 0.7 wt% solution of example 2 part (b) and 50 g of 1.2 wt% solution of example 2 part (c)
were mixed together and the pH adjusted to 5 using 0.1M NaOH. The 2 wt % dispersion
iron oxide maintained at the same pH was then added to the macro-RAFT blend. The mixture
was vigorously stirred for 2 hours at room temperature before the pH was adjusted to 7.0.
mixture was then left stirring for another 3 hours. At this pH the 00polymer remained partially
neutralized while the nanoparticles were sufficiently above their point of zero charge to also be
stable. The dispersion was then dialysed to remove salts, residual solvents. unwanted low
molecular weight reactiOn side products and unbound polymer. Bigger particles in the
dispersion Were removed by ultracentrifugation. The d nanoparticle dispersion was then
distilled to increase the solids loading in the aqueous ferrofluid dispersion to about 70 wt%.
The resulting aqueous ferrofluid was found to be stable in phosphate buffered saline solution.
Part (e): Modification ofstabllisersfor iron oxide particles ofexample 2 par! (d)
Into coated nanoparticles prepared from example 2 part (d) (7.8 g), N-
hydroxysuccinimide (NHS, 14.4mg) and then 1-Ethyl(3-Dimethylamino-
propyl)carbodiimide (EDAC, 20 mg) were added, mixed by shaking and allowed to react for 2
hours at room temperature. A solution of e (90 mg of 2,2’-(Ethylenedioxy)bis-
-53..
(ethylamine) in 1 ml of water) was then added to the reaction mixture and allowed to react for
dialysed water with numerous
a further 3.5 hours. The on was then against excess
changes, to remove free EDAC and the reaction lay—products.
EXAMPLE 3
Steric stabilization of iron oxide nanoparticles in aqueous dispersion using the uid
of example 1 part (a) and the poly(monoacryloxyethyl phosphate)w~block-poly(ethylene
oxide)" macro raft agent of e 2 part (b)
Nanopanicle dispersion (8.0 g) prepared according to example i part (a) was diluted
with 50g of MQ water to yield a 0.5 wt% sion of the nanoparticles. The pH of this
prepared nanoparticle dispersion was then raised to S. The 0.5 wt °/o dispersion of iron oxide
maintained at the same pH was then added to the 50 g of macro~RAFT agent from example 2
the pH was
part (b). The mixture was vigorously stirred for 2 hours at room temperature before
adjusted to 7.0. The mixture was then left ng for another 3 hours. At this pH the
mer remained partially neutralized while the nanopartieies were sufficiently above their
point of zero charge to also be stable. The sion was then ed to remove salts.
residual solvents. unwanted low molecular weight reaction side products and unbound
polymer. The final solids of the sion was 0.74%.
EXAMPLE 4
Steric stabilization of iron oxide nanoparticles of the aqueous ferrofluid of example 1
part (3) using the poly(monoacryloxyethyl phosphate ),o.block-poly(acrylamideizo macro-
‘raft agent of example 2 part (c)
Nanoparticle dispersion prepared in example I part (a) (6.!9 g)‘ was diluted with MQ
water (100 g) to yield a l wt% dispersion of the nanoparticles, The pH of this nanoparticle
sion was then raised to 5 using 0.l M sodium hydroxide. The 2 WI% dispersion of the
iron oxide dispersion was then added to the macro-RAFT copolymer soluti0n from e 2
before the
part (c) (50 g). The mixture was stirred vigorously with an overhead stirrer 2 hours
pH was adjusted to pH 7 using sodium hydroxide solution. The mixture was then left to stir
vigorously for another '12 hours at room temperature. The nanoparticle dispersion was then
dialysed to remove salts, residual solvents, unwanted low molecular weight reaction side
3O products and unbound polymer. The solid content of the final dispersion is 0.71%.
EXAMPLE 5
the aqueous
Steric stabilization oi'iron Oxide nanoparticles in aqueous dispersion from
ferrofluid of example 1 part (a) using 100% amine modified poly(monoacryloxyethyl
phosphate)w-block-poly(acrylamide)zo
Part (a): Preparation of amine modified pab:(mon0acryloxyethyl ate)!0-block-
. poly(acrylamide)20 macro-RAFT agentfrom the macro-RAFT agent ofexample 2 part (c)
N-hydroxy succinimide 98% (0.64 g), 2. 2’«(Ethylenedioxy)bis—(ethylamine), _98%
(0.54 g) was added to 30.0 g of poly(monoacryloxyethyl phosphateho-blockpoly
(acrylamide)zo block copolymer of example 2 part (c) at pH 6.25 in a 100 mL glass .
The bottle was sealed with parafilm and placed on a roller for mixing for 2 hours. After 2
hours, the mixture had a pH of 8.l2 to yield the Nl-lS-activated carboxyl groups which are
reactive towards primary amine. l.26 g of N-(3~Dimethylaminopropyl)-N'-ethy|carbodiimide
hydrochloride was then added to the mixture, which was left on the roiler for r 12 hours.
The excess N-(3~Dimethylaminopropyl)-N'-ethyIcarbodiimi'de hydrochloride was removed by
dialysis.
Part (b): Preparation .of sterically stabilized iron oxide nanoparticles from the aqueous
ferrofluid ofexample 1, part (a) and the macro—RAFT agent ofexample 5, part (a)
NanOparticle dispersion prepared in example 1 part (a) (8.38 g) was diluted with MQ
water (50 g) to yield a 0.5 wt% dispersion of the nanoparticles. The pH of this nanOparticle
diSpérsion was then raised to 5 using 0.1 M sodium ide. The 0.5 wt% dispersion of the
iron oxide nanoparticles was then added to the macro-RAFT copolymer solution, from
example 5 part (a) (22.6 g) and 50 g of MQ'water. The mixture was stirred vigorously with an
overhead stirrer for 2 hours before the pH was ed to pH 7 using sodium hydroxide
on The mixture was then left to stir vigorously for r 10 hours at room temperature.
The nanoparticle dispersion was then dialysed to remove salts, residual solvents, ed low
molecular weight on side products and unbound polymer. The solids content of the
dialysed aqueous ferrofluid sion was 0.36%.
EXAMPLE 6
Steric stabilization of iron oxide nanoparticles in aqueOUS dispersion using 95%
poly(monoacryl0xyethyi phosphate)w-block-poly(acrylamidem macro-raft agent of
example 2 part (c) and 5% amine modified poly(monoacryloiryethyl phosphate)m-block-
poiy(acrylamide)m of example 5 part (a)
Nanoparticle dispersion ed in example l part (a) (8.09 g) was d with MQ
water (50 g) to yield a 0.5 wt% dispersion of the nanoparticles. The pH of this nanoparticle
0.5 wt% dispersion of the
dispersion was then raised to 5 using 0.1 M sodium hydroxide. The
solution which was pH
iron oxide dispersion was then added to the RAFT copolymer
.0 from example 5 part (a) (1.7 g), example 2 part (c) (1.0 g) and 50 g of MQ water. The
the pH was adjusted
mixture was stirred vigorously with an overhead stirrer for 2 hours before
solution. The mixture was then left to stir vigorously for
to pH 7 using sodium hydroxide
then dialysed to remove
r 3 hours at room ature. The rticle diSpersion was
and unbound
salts, residual solvents, unwanted low molecular weight reaction side products
polymer. The solids content of the ed aqueous ferrofluid dispersion is 0.53%. ‘
EXAMPLE 7
Steric stabilization of iron oxide nanoparticles in aqueous di5persion using
poly(monoacryloxyethyl phosphate)w-block-polflacrylamidem macro raft agent
Part (a): Preparation ofdiluted aqueous/errofluid stable in acidic medium
Magnetite nanoparticles were produced following the method of Massart (Preparation
of aqueous magnetic liquids in alkaline and acidic media. lEEE Transactions on ics,
1981. MAG-l7(2): p. 1247-1248). An s e of ferric and ferrous chlorides was
added to ammonia solution. The resulting precipitate was isolated by centrifugation then
oxidised to maghemite by mixing with iron e solution and heating. The precipitate was
then washed in 2 molar nitric acid then finally peptised by water to form a dilute aqueous
ferrofluid of approximately 5 wt% solids.
Part (1)): Preparation of a poly(monoacryloayetltyl phosphate)10~block-poly(acrylamide)60
RAFT agent using 2-{[(butylsuyanyvcarbonothtoyllsulfanylf propanoic acid.
A solution of 2-{[(butylsulfanyl)carbonothioyI]sulfanyl} propanoic acid (0.26 g, Ll
mmol), 4,4‘-azobis(4-cyanovaleric acid) (0.06 g. 0.2 mmol). acrylamide (4.73 g, 66 mmol) in
dioxane (10 g) and water (10 g) was prepared in a 100 mL round bottom flask. This was stirred
magnetically and sparged with nitrogen for IS minutes. The flask was then heated at 70°C for
4 hrs. At the end of this period, monoacryloxyethyl phosphate (2.17 g, 11.! mmol) and 4.4’-
azobis(4-cyanovaleric acid) (0.06 g, 0.2 mmol) were added to the flask. The mixture was
deoxygenated and heating was continued at 80°C tor a further 12 hours. The copolymer
solution had 24% solids. The mer solution was then d with MQ water to 0.7 wt%
3O and the'pH adjusted to 5 using 0.1M NaOH.
- Part (c): Preparation of sterically stabilized iron oxide nanoparticles from the aqueous
ferrofluid ofpart (a) and the macro-RAFT agent ofexample 7part (b).
Nanoparticle dispersion prepared in example 7 pan (a) (40 g) was diluted with MQ
water (200g) to yield 'a l wt% dispersion of the nanoparticles. The pH of this nanoparticic
dispersion was then raised to 5 using 0.l M sodium hydroxide. The lwt°/o sion of the
iron oxide dispersion was then added to the macro—RAFT mer solution from part (b)
(200 g). The mixture was stirred vigorously with an overhead stirrer for 45minutes before
pH was ed to pH 7 using sodium hydroxide solution. The mixture was then left to stirr
vigorously for another 2 hours at room temperature. The nanoparticle sion was then
dialysed to remove salts, residual solvents, unwanted low molecular weight reaction side
products and unbound polymer. Bigger particles in the dispersion were removed by
ultiacentrifugation. The purified nanoparticie dispersion was then distilled to increase the
solids loading in the aqueous luid dispersion to about 70 wt%.
Steric stabilization of sigma ludox as 30 silica particles using 95% poly/[2-
(dimethylamino)ethyl methacrylatelio-bloek-polflethylene oxide)" macro raft agent and
5% poly(2-(dimethylamino)ethyl rylate)w~block-poly(acrylamidem macro raft
agent
Part (0): Preparation ofa poly/2-(dimetlxylamino)ethyl methacrylate]!0-block-pobr(erhylene
! 7 macro-RA‘FT agent based on 2-{/butylsulfany!)carbonothioyll-suq'anylfpropanoic
acid.
A solution of 80 from example 2 part (a) (l .38 g, 1.4 mmol), 4.4‘-azobis(4-
cyanovaleric acid) (0.08 g, 0.3 mmol), ethylamino)ethyl methacrylate (2.l3 g, 13.6
mmol) in dioxane (10 g) and water (5 g) was prepared in a 100 mL round bottom flask. This
was stirred magnetically and sparged with nitrogen for 15 minutes and the reaction was carried
out at 70°C for a 12 hours. The copolymer solution had 18.4% .
Part (b): Selective quaternization of a poly[2-(dimerhylaminokrhyl methacrylate/ID—block-
poly(ethylene oxide)! 7 macro-RAFT agent based on 2-{{butylsulfanyl)carbonolhioyll—
sulfanyl}propan0ic acid.
Example 8 part (a), l6.5 g was diluted with MQ water (17 g) and methyl iodide (0.7 g)
added. The mixture was stirred at room temperature for 1 hour before being partially dried
3O using a rotary evaporator. The dried samples were then placed in the vacuum oven to dry the
macro raft agent which yielded l00% solids.
Part (0): Preparation of a poly(2-(Dimerhylamino)ethyl methacrylare) 10-bIock-
crylamide)25 macro-RAFT agent based on tylsulfanyl)carbonothioyl];
sulfanylfpropanoic acid. .
A on of 2-{[(butylsulfanyl)carbonothioyllsulfanylipropanoic acid (0.6 g. 2.6
mmol), zobis(4—cyanovaleric acid) (0.11 g, 0.4 mmol), acrylamide (4.45 g, 62.7 mmol)
in dioxane (18.8 g) and water (10.5 g) was prepared in a 100 mL round bottom flask. This was
stirred magnetically and sparged with nitrogen for IS minutes. The flask was then placed in a
709C oil bath for 4 hrs. The homopolymer solution had 32.7% solids. All of the hom0polymer
solution obtained, 2-(Dimethylamino)ethyl methacrylate (3.94 g, 25.1 mmol) and 4.4‘-
(4-cyanovaleric acid) (0.088 g, 0.32 mmol) were added to a mom. round bottom flask.
The mixture was deoxygenated for £5 minute and placed in a 70°C oil bath for 12 hours. The
final solids ofcopolymer solution was 26.9%.
Part (d): Selective quaternization of a poly(2~(dimethylamino)ethyl methacrylateNU-ltlock-
pobr(acrylamide)25 RAFT agent based on 2-{/butylsulfanyl)carbonothioyll-
sulfanyl}propanoic acid.
e 8 part (c) (I93 g) was diluted with MQ water (20 g) and methyl iodide (0.78
g) was added. The mixture was stirred at room temperature for l hour be partially dried using a
rotary evaporator.. The partially dried samples was then placed in the vacuum oven to dry the
macro rah agent which yield l00% solids.
Part (e): Preparation ofsterically stabilized Sigma Ludox A530 silica particles using a 95:5
blend ofthe macro-RAFT agents ofexample 8 part (b) and example 8 part (d)
Ludox A830 from Sigma Aldrich (2.5 g) was diluted with MQ water (100 g) to yield a
2 wt% dispersion of the nanOparticles and the pH is 9.62. A mixture of example 8 part (b)
(0.96 g) and of example 8 part (d) (0.0653 g) was dissolved in MQ water (50 g) and the pH
was 7.59. The 2 wt% dispersion was then poured into the e of macro-Raft agents. The
mixture was vigorously stirred for 5 hours at room temperature. The dispersion was then
ed to remove salts, residual solvents. unwanted low molecular weight reaction side
products and unbound polymer. The solid content of the dialysed silica sol sion was
0.69%. The pH ofthe sample was adjusted to 6.76 with sodium hydroxide solution.
Part 0): Modification ofstabilisersfor silica particles ofexample 8 part (e) [EP341070A]
Sterically stabilised silica sol particles prepared from example 8 part (e) (60g). N-
hydroxysuccinimide (NI-ls, 39.4mg) and then l-Ethyl(3-Dimethylamino-
pr0pyl)carbodiimide (EDAC, 56.2mg) were added, mixed by shaking and allowed to react for
2 hours at room temperature. 37mg of2,2’-(Ethylenedioxy)bis-(ethylaminc) was then added to
W0 2012/142669
the on mixture and allowed to react for a further 12 hours. The solution was then dialysed
against excess water with numerous changes, to remove free EDAC and the reaction by-
products.
EXAMPLE 9
Steric stabilization of sigma ludox as40 silica sol using 95% polyl2—(dimethylamino)ethyi
methacryiate]io—block—polflethylene oxide)" macro raft agent and 5% poly(2-
hylamino)ethyl methacrylate).o-block-poly(acrylamide)2s macro raft agent
Part (0): Preparation of sterically stabilized Sigma Ludox A530 Silica particles and a 95:5
blend oftlre RAFT agents ofexample «Spar! (b) and e 8 part (d)
Ludox A840 from Sigma Aldrich (5.0g) was diluted with M0 water lOOg to yield a 2
wt% sion of the nanoparticles and the pH is 9.97. A mixture of macro-RAFT agents,
which consisted of example 8 pan (1)) (1.72 g) and example 8 part (d) (0.13 g) was dissolved in
100 g of M0 water and the pH was 7.95. The 2 wt% dispersion was then poured into the
mixture of macro-RAFT agents. The mixture was vigorously stirred for 5 hours at room
temperature. The dispersion was then dialysed to remove salts, residual solvents, unwanted
low lar weight reaction side products and unbound polymer. The solid content of the
dialysed silica sol dispersion is 1.45 %. The pH of sample was 7.65.
Parr (b): Modification ofstabilisers ofsilica particles ofexample 9 part (a)
To sterically stabilised silica sol particles prepared in example .9 part (a) (30 g), N-
hydroxysuccinimidc (NHS, 11.6 mg) and i—Ethyl(3-Dimethylamino-propyl)carbodiimide
‘(EDAC. 16.6 mg) were added, mixed by shaking and allowed to react for 2 hours at room
temperature. 2,2'-(Ethylenedioxy)bis-(ethyIamine) (45.1 mg) was then added to the reaction
mixture and d to react for a further 12 hours. The solution was then dialysed against
excess water with numerous changes. to remove free EDAC and the reaction by-products.
EXAMPLE 10
Steric stabilization of 130 nm silica particles using poly(2-(dimethylamino)ethyl
methacrylate)m-block-poly(acrylamide)25 macro raft agent
Part (a): Silica les were prepared using the s of Costa et at.
(Carlos A. R. Costa, Carlos A. P. Leite. and do Galembeck J. Phys. Chem. B.
2003, 107 (20), 4747-4755.) to obtain l30 nm diameter silica particles at 0.18 % solids in
wate i'.
part
Part (b): Steric stabilization of the 130 nm diameter silica particles of example (it)
using the RA FT agent ofexample 8 part (d)
Silica particle sion of example 10 part (a) (l l .IS g) was diluted with MQ water
(20 g) Macro-RAFT
to yield a 0.! wt% dispersion of the nanopanicles with a pH of 9.26.
in 25g of M0. water (25 g) to yield a agent of example 8 part (d) (0.023 g) was ved
solution of pH 5.80. The silica sion and the macro—RAFT solution were then blended and
vigorously stirred for 5 hours at room temperature. The dispersion was then centrifuged to
remove salts, residual solvents, unwanted low molecular weight reaction side products and
unbound polymer. The solid content of the sterically stabilised silica dispersion is 0.8] %.
EXAMPLE 11
Steric ization of the 130 nm diameter silica particles of example 10 part (3) using
the “grow from” approach.
The silica particles of example 10 part (a) were RAFT functionalised using 6-
(Triethoxysilyl)hexyl 2-(((Methylthio)carbonothioyi)—2-phenylacetate and r chains
comprising poly methoxy—PEG acrylate (Aldrich .454 g/ mol) were grown from the surface of
the particles according to the methods of Ohno et al. (Kohji Ohno. Ying Ma, Yun Huang,
Chizuru Mori, Yoshikazu Yahata, Yoshinobu Tsujii, Thomas eyer, John Moraes. and
Sébastien Perrier oleCules, 20] l, 44 (22), pp 894443953.) The molecular weight
obtained for each ed chain was approximately 56.000 g/mol. The final particles were
obtained in water at a solids content of to mg/mL and the particle size was 258 nm. as
measured by DLS.
EXAMPLE 12
Steric stabilization of 10—15 nm gold nanoparticles in aqueous diSpersion using 95%
thylene oxide)" macro raft agent and 5% poly(acrylamide)m macro raft agent
Part (a): Synthesis of 10—15 am citrate stabilized gold nanopartr‘cles stable in aqueous
medium
Citrate-stabilized gold nanoparticles (IO-l5 nm) were prepared using Frens' method
(Frens, G. Nat. Phys. Sci. 1973, 24!, 20-2.) Briefly, all glassware was first washed with an
aqua regia solution (25 vol % trated nitric acid and 75 vol % concentrated hydrochloric
acid), then rinsed with Milli-Q water several times, and dried. 100 ml of an aqueous solution
containing tertrachloroaureic(lll) acid rate (0.0!g, 0.025mmol) was refluxed in a 500
mL 3-necked round bottom flask. 2 ml solution of trisodium citrate dihydrate (0.02 g. 0.068
mmol) was added to it. The solution was heated to boiling point vigorous stirring. Boiling and
2012/000414
vigOrous stirring was maintained for 30 min. A progressive change of colour from yellow to
wine red was observed. The solution was cooled down. dialysed to get rid of excess sodium
citrate and stored in at 5°C. The rticie concentration in the dispersion was 50 ppm.
Part‘ (b): Preparation of a crylamide)20 macro—RA FT agent using: 2-
{llbutylsulfanybcarbonothioyl/salfanyl}propanoic acid.
A solution of 2-{[(butyisulfanyl)carbonothioyl]sulfanyl} propanoic acid (0.7l g, 3.0
mmol), zobis(4-cyanovaleric acid) (0.04 g, 0.15 mmol), acrylamide (4.28 g, 60.2 mmol)
in dioxane (7.5 g) and water (7.5 g) was prepared in a 100 mL round bottom flask. This was
stirred magnetically and sparged with nitrogen for 15 minutes. The flask was then placed in a
70°C oil bath with continued stirring for 4 hrs. The polymer solution had 25. l7% .
Part (c): Preparation of sterically stabilized 10-15 am gold nanoparti'cles from the citrate
stabilised gold nanoparticles of example 12 part (a) and a 95:5 blend of the macro-RAFT .
agent of example 2 part (a) and the macro-RAFT agent ofexample 12 part (b).
lOO ml gold nanoparticle dispersion (50 ppm) of e 12 part (a) was transferred to
a 250 ml round bottom flask. A 10 ml solution ning 0.0l2 g of the RAFT agent of
example 2 part (a) and 0.l5 g the macro-RAFT agent of example 12 part (b) was then added.
The mixture was stirred vigorously with a magnetic stirrer bar for 2 hours at room temperature
and then ed to remove salts, residual solvents, unwanted low molecular weight reaction
side products and unbound polymer. The purified nanoparticle dispersion was at a
concentration of 50 ppm and was stored in the fridge at 5°C. The resulting aqueous
nanoparticle dispersion was found to be stable in phosphate buffer saline solution,
Part (d): Modification ofstabilisersfor gold nanoparticles ofexample 12 part (c)
Into coated nanoparticles prepared from example 12 part (c) (IOO ml), N-
hydroxysuccinimide (NHS, 4mg) and then l~Ethyl(3-Dimethylamino-propyl)carbodiimide
(EDAC. 4.l mg) were added, mixed by shaking and allowed to react for 2 hours at room
temperature. A solution of diamine (21mg of2,2’-(Ethylenedioxy)bis-(ethylamine) in 2 ml of
water) was then added to the reaction mixture and allowed to react for a further 3.5 hours. The
solution was then dialysed against excess water with numerous changes, to remove free EDAC
and the reaction by-products.
EXAMPLE 13
Steric stabilization of 3-8 nm gold nanoparticles dispersed in aqueous medium using thiol
modified poly(acrylamide)20
Part (a): Thiol modification ofpoly(acrylamide)20 macro-RAFT agent ofpart example 12
part (b) using isopropyl amine.
A solution of the poly(acrylamide)2o macro-RAFT agent of example l2 part (b) (lg,
0.6 mmol), isopropyl a'm'me (L77g, 30 mmol) in dioxane (7.5 g) and water (7.5 g) was
prepared in a 100 mL round bottom flask. This was stirred ically and sparged with
en for l5 minutes, then d to react for a 24 hours at 25°C. At the end ofthis period,
the polymer was precipitated in diethyl ether (50 ml). The precipitates were separated from the
on e by filtration and dried under yacuum using a rotary evaporator. The dried
thioi terminated poly(acrylamide)zo was d with nitrogen for IS minutes and stored in an
airtight container at 20°C.
Parr (b): Preparation ofsterically stabilized 3-8 nm gold nanoparticles in aqueous dt'Spersr'on
using thiol ed poly(acntlamide)20 ofexample 13 part (a).
Milli-Q water (250 mL) was refluxed in a 500 mL ed round bottom flask. 25 mL
of a aqueOUS solution containing tertrachloroaureic(lll) acid trihydrate (0.057! g, 0.1444
mmol) was then added and the solution heated to boiling. Then, a solution in water (25 mL) of
tris‘odium citrate dihydrate (0.5 g, 1.7 mmol) and thiol modified poly(acrylamide)zo (O.l2 g,
0.0779 mmol) of example .13 part (a) was added and the reaction carried out for 2 hours at
°C. By the end of this period, the colour of the on had turned from yellow to wine red.
The molar ratio of steric stabilizer to the tettrachloroaureicflli) acid trihydrate in this case is
0.5. The gold nanoparticles were ted from the dispersion by centrifugation at 52,000 g
for 30 min. The rticles were redispersed in MillioQ water at a concentration of I90 ppm.
The size of gold nanoparticles obtained from TEM was 3-8 nm.
EXAMPLE l4
Steric stabilizatiOn of 8-10 nm gold nanoparticles dispersed in aqueous medium using
thiol modified poly(acrylamide)zo of example 13 part (a)
Milli-Q water (250 mL) was refluxed in a 500 mL 3-necked round bottom flask. 25 mL of an
aqueous solution containing tertrachloroaureic(lll) acid trihydrate (0.0652 g, 0.16 mmol) was
added and the solutiOn was heated to boiling. Then, a solution in water (25 mL) of trisodium
citrate dihydrate (0.5 g, l.7 mmol) and thiol modified poly(acrylamide)zo (0.022 g, 0.0l42
mmol) of example 13, part (a) was added and allowed to react for 2 hours at 25°C. By the end
‘30 of this period, the colour of the solution had turned from yellow to wine red. The molar ratio of
steric stabilizer to the tertrachloroaureic(lll) acid trihydrate in this case was 0.09. The gold
nanoparticles were separated from the dispersion by centrifugation at 52.000 g for 30 min. The
W0 2012/142669 2012/000414
-52.
nanoparticles were redispersed in Milli-Q water at a concentration of 390ppm. The size of gold
nanoparticles obtained from TEM was 8-10 nm.
EXAMPLE )5
Steric ization of 30—40 nm gold nanoparticles dispersed in aqueous medium using
thiol modified poly(acrylamide)2o of example l3 part (a)
Part (a): Synthesis of 30—40 am citrate stabilized gold nanoparticles stable in aqueous
medium.
Citrate-stabilized gold nanoparticles (30-40 nm) were prepared using Frens method
(Frans. G. Nat. Phys. Sci. 1973, 241, 20—2.) Briefly, all glassware was first washed with an
aqua regia solution (25 vol % concentrated nitric acid and 75 vol % concentrated hydrochloric
acid), then rinsed with Milli-Q water several times. and dried. 100 ml of an aqueous solution
containing tertrachloroaureic(lll) acid trihydrate (0.0lg, mol) was refluxed in a 500
mL 3-necked round bottom flask. 1 ml solution of ium citrate dihydrate (0.0] g, 0.034
mmol) was then added. The solution was heated to boiling with vigorous ng. Boiling and
vigorous stirring was maintained for 30 min. A progressive change of colour from yellow to
winered was observed. The solution was cooled to ambient, ed to get rid of excess
sodium citrate and stored at 5°C. The nanoparticle concentration in the dispersion was 50 ppm.
Part ([2): Preparation ically stabilized 30-40 am gold nanoparticles from the aqueous
gold nanoparticle dispersion ofexample {5 part (a) and thiol ed poly(acrylamide)20 of
example 13 part (a).
l00 ml gold nanOparticle dispersion (50 ppm) of example 15 part (a) was taken in a
250 ml round bottom flask. 10 ml solution of aqueous solution of example l3 part (a)
containing thiol modified poly(acrylamide}zo 8 g, 0.0044 mmol) was then added. The
mixture was stirred vigorously with a magnetic stirrer bar for 2 hours at room ature and
then dialysed to remove salts, residual solvents, unwanted low molecular weight reaction side
products and unbound polymer. The purified rticle dispersion was then distilled to
increase the solids loading in the aqueous nanoparticle dispersion to l92ppm. The resulting
aqueous nanoparticle dispersion was found to be stable in phosphate buffer saline solution,
EXAMPLE 16
3O Synthesis of polystyrene nanOparticles in s dispersion using poly(styrene)9-b-
poly(acrylamide).5 macro raft agent
Part (a): Preparation of self assembled poly(styrene)9-b-poly(acrylamide)15 macro-RAFT
agent using: 2—{[(butylsalfanyl)carbonothioyllsulfanylfpropanoic acid.
WO 42669
.
3.36 A solution of 2—{[(buty1sulfanyl)carbonothioy1]suli‘anyl)propanoic acid (0.80 g,
mmol). 4.4’-azobis(4-cyanovaleric acid) (0.10 g, 0.36 mmol). acrylamide (3.71 g, 52.06
mmol) in dioxane (6.61 g) and water (4.41 g) was prepared in a 50 mL round bottom flask.
This was stirred magnetically and sparged with nitrogen for 10 s. The flask was then
heated at 70°C for 5 hrs to produce the clear homopolymer solution. At the end of this ,
styrene (3.16 g, 30.3 mmol), '4,4’-azobis(4-cyanovaleric acid) (0.19 g, 0.69 mmol), dioxane
(21.15 g) and water (614 g) were added to the flask. The mixture was Stirred, dcoxygenated
with nitrogen for 10 minutes. The flask was then immersed back in an oil bath at 70°C for
overnight with constant stirring.
Part (6): Synthesis styrene uanopartt‘cles using the selfassembled macro-RAFT agent
prepared in example 16 part (a) _
To a clear dispersion of macro-RAFT agent from example 16 part (a) (1.00 g) in a 50
mL round bottom flask on a magnetic stirrer, sodium hydroxide solution (1.94 g of 0.3%
solution, 0.15 mmol with water (22.1 g)) was added drop wise. To this mixture styrene (1.109
g, 10.5 mmoi) Was added and stirred ght. 4,4'-azobis(4-cyanovaleric acid) (15.5 mg,
0.055 mmol) and sodium hydroxide solution (1.04 gof 3% soiution, 0.78 mmol) were added.
The flask was stirred for 2 hours, then sealed and subsequently deoxygenated with nitrogen
sparging for 10 minutes. The whole flask was immersed in an oil bath with a temperature
setting of 80°C and maintained at that temperature for 5 hours under constant magnetic stirring.
The latex contained particles with average diameter of 15 nm by zer light scattering. The
latex was ed against Q water to remove impurities.
EXAMPLE 17
Synthesis of polystyrene nanoparticles in aqueous dispersion using self assembled '
poly(styrene)9-b-poly(acrylamideho macro raft agent of example 16 part (a)
Part (0): Further growth of the selfassembled macro-RAFT agent ofexample I6 part (a) to
form poly(styrene)52~b-poly(acrylamide)20 macro-RAFT. ,
To a clear dispersion of RAFT agent from example 16 part (a) (1.02 g) in a 25
mL round bottom flask on a magnetic'stirrer. sodium hydroxide solution (0.44 g of 3%
on, 0.33 mmol), zobis(4-cyanovaieric acid) (14.1 mg, 0.05 mmol) and water (14.0
'30 g) were added and stirred to dissolved. To this mixture styrene (0.61 g, 5.85 mmol) was added
and stirred overnight. The flask was then sealed and subsequently deoxygenated with nitrogen
sparging‘ for 10 minutes. The whole flask was immersed in an oil bath with a temperature
~64~
setting of 70°C and maintained at that temperature for 6 hours under constant magnetic stirring.
A clear diSpersion was obtained
Part (b): Synthesis of polystyrene nanOpam‘cIes using the‘macro-RAFT agent dispersion
prepared in example 17 part (a)
To a clear solution of macro-RAFT agent from e l7 part (a) (6.09 g) in a 50 mL
round bottorn flask on a magnetic stirrer, sodium hydroxide on (0.36 g of 3% solution,
0.27 mmol), 4,4’-azobis(4-cyanovaleric acid) (26.6 mg, 0.095 mmol), styrene (0.45 g, 4.37
mmol) and water (8.31 g) were added. The flask was stirred for 5 hours, then sealed and
subsequently deoxygenated with nitrogen ng for 10 minutes. The whole flask was
immersed in an oil bath with a temperature setting of 70°C and maintained at that temperature
for overnight under constant magnetic stirring. The latex contained particles with mean
diameter of 47 nm by Zetasizer light scattering. The latex was ed against miIIi-Q water to
remove impurities.
EXAMPLE 18
Synthesis of polystyrene nanoparticles in aqueous sion using po|y(acrylamide)zo
macro raft agent
Part (a): Preparation of poly(acrylamide)20 RAFT agent using: 2-
{[(butylsulfanylkarbonothioyljsuyanylfpropanoic acid.
A solution of 2~{[(butylsulfanyl)carbonothioyI]sulfanyl}propanoic acid (0.73 g, 3.08
mmol), 4,4’-azobis(4-cyanovaleric acid) (0.07 g, 0.3 mmol), acrylamide (4.30 g, 60.5 mmol)
in dioxane (15 g) and water (7.5 g) was prepared in a 100 mL round bottom flask. This was
stirred magnetically and sparged with nitrogen for 15 minutes. The flask was then heated at
70°C for 4 hrs to produce the clear homopolyrner soiution.
Parr(b): Synthesis ofpolystyrene nanopam'cles using the maéro-RAFT agent prepared in
example 18 part (a)
A clear solution of macro-RAFT agent from example 18 part (a) (1.05 g), sodium
hydroxide (2.07 g of 3% solution, 1.55 mmol) and water (12.16 g) was prepared in a 25 mL
. round bottom flask, stirring on a magnetic stirrer. To this solution 4,4’-azobis(4-cyanova|eric
acid) (13.6 mg, 0.049 mmol), dioxane (1.1 g) and styrene (1.125 g, 10.8 mmol) were added.
The mixture was stirred for 2 hours to obtain an emulsion like mixture. The flask was sealed
and subsequently enated with nitrogen sparging for 10 s. The whole flask Was
immersed in an oil bath with a temperature setting of 70°C and ined at that temperature
for overnight under constant magnetic stirring. The latex contained les with average
:65.
diameter of 200nm by Zetasizer light scattering. The latex was dialysed against milli-Q water
to remove impurities.
EXAMPLE l9
Stabilisation of iron oxide nanoparticles with dextran from leuconostoc mesenteroides
(average molecular weight of 9000-1 1,000, sigma aldrich) coated particles. (example 19 is
a comparative example)
ml of 0.5 M FeCl2/4H20 and 25ml of IM FCC13/6H20 were mixed and
magnetically stirred in a 500 ml 3 neck round bottom flask. The resulting solution was diluted
by adding 100 ml of MQ water and placed in an oil bath at 70°C. Dextran solution (50 ml of
IO lS% solids in water) was added and the solution maintained in the oil bath for 10 minutes.
Ammonia solution (30 ml, 28%) was then added and the mixture kept at 70°C for a further 45
minutes. The reaction product was cooled to room temperature and dialysed t MQ water
to remove excess ammonia. The water was changed at least three times. Larger aggregates
were removed by magnetic ntation. Volume was reduced to about 100 ml by removing
water on rotary evaporator. The final dispersion was sonicated at 70% AMP using an
ultrasonicator for 10 minutes and at also at 30% AMP for 30 minute.
EXAMPLE 20
Steric stabilization of iron oxide nanoparticles of example 1 part (a) using 50%
poly(monoacryioxyethyl phosphate)io~block—poly(ethylene oxideln macro raft agent of
example 2 part (b) and 50% amine d poly(monoacryloxyethyl phosphate).o-block-
poly(acrylamid8)zo macro raft agent
Part (a): ation of stert'cally stabilized iron oxide nanopartt'cles from the aqueous
ferroflm'd of example 1 part (a) and a 50:50 blend of the macro-RAFT agent of example 2
part (b) and the macro-RAFT agent ple 2 part (c).
Aqueous ferrofluid prepared according to example 1, part (a) (8.!0 g) was diluted with
MQ water (50 g) to yield a 0.5 wt% diSpersion of the nanoparticles. The pH of'this prepared
rticle dispersion was then raised to 5. A blend of macro-RAFT which consist of 50 g of
at 5-.l wt% , 3.3 wt% of which was the macro-RAFT agent of example 2 part (b) and i8
wt% of which was the macro-RAFT agent of example 2 part (c) were mixed together and the
pH adjusted to 5 using 0.iM NaOH. The dimension of iron oxide. maintained at the same pH
was then added to the RAFT blend. The mixture was usly stirred for 2 hours at
r00m ature before the pH was adjusted to 7.0. The mixture was then left stirring for
another 12 hours. At this pH the copolymer remained partially neutralized while the
2012/000414
nanoparticles were sufficiently above their point ’of zero charge to also be . The
diSpersion was then dialysed to remove salts, residual solvents, unwanted low molecular
weight on side products and unbound polymer. The solid content of the dialysed aqueous
uid dispersion is 0.6%.
Part (f): Modification ofstabilisersfor iron oxide particles ofexample 20 part (a)
Into coated nanoparticles prepared from example 20 part (a) (703), N-
hydroxysuccinimide (NHS, 89.3mg) and then l-Ethyl-3—(3-Dimethylamino-
propyl)carbodiimide (EDAC, 127mg) were added, mixed by g and allowed to react for 2
hours at room temperature. 29lmg of 2,2’-(Bthylenedioxy)bis-(ethylamine) was then added to.
the reaction mixture and allowed to react for a further 12 hours. The solution was then dialysed
t excess water with numerous changes, to remove free EDAC and the reaction byproducts.
EXAMPLE 2!
Steric stabilization of iron oxide nanoparticles of example 1 part (a) using 80%
poly(monoacryloxyethyl phosphate)w-block—poly(ethylene oxide)” macro raft agent of
example 2 part (b) and 20% amine modified poly(monoacryloxyethyl phosphatem'block-
. poly(acrylamide)2o macro raft agent
Part (11): Preparation of stert‘cally ized iron oxide nanopam’ctes from the aqueous
ferrofluid ofexample 1 part (a) and a 80:20 blend of the RAFT agent of example 2
part (b) and the macro-RAFT agent ofexample 2 part (c).
Aqueous ferrofluid prepared'according to example 1, part (a) (8. l0 g) was diluted with
MQ water (50 g) to yield a 0.5 wt% dispersion of the nanoparticles. The pH of this prepared
rticle dispersion was then raised to 5. A blend of macro-RAFT which consist of 50 g of
at 6.0 wt% solids, 5.28 wt% of which was the macro-RAFT agent of example 2 part (b) and
0.72 wt% of which was the macro-RAFT agent of example 2 part (c) were mixed together and
the pH adjusted to 5 using 0.lM NaOH. The sion of iron oxide, maintained at the same
pH was then added to the macro-RAFT blend. The e was vigorously stirred for 2 hours
at room temperature before the pH was ed to 7.0. The mixture was then left Stirring for
another 12 hours. ,At this pH the cepolymer remained partially neutralized while the
3c nanoparticles were sufficiently above their point of zero charge to also be stable. The
dispersion was then dialysed to 'remove salts, residual solvents, unwanted low molecular
weight reaction side products and unbound polymer. The solid content of the dialysed aqueous
ferrofluid dispersion is 0.7%.
WO 42669
Part (b): cation ofstabilisersfor iron oxide particles of example 21 part (a)
late coated nanoparticles prepared from example 2, Part (C) (60g), N-
hydroxysuccinimide (NHS, 39.4mg) and then l(3 -Dimethylamino~
pr0pyl)carbodiimide (EDAC, 56.2mg) were added, mixed by shaking and allowed to react for
2 hours at room temperature. 130mg of 2,2‘-(Ethylenedioxy)bis-(ethylamine) was then added
to the reaction mixture and allowed to react for a further l2 hours. The solution was then
dialysed against excess water with numerous changes, to remove free EDAC and the reaction
by-products.
E 22
Steric stabilization of iron oxide nanoparticles of example 1 part (a) using 90%
poly(monoacryloxyethyl phosphate).o-block~poly(ethylene oxidchv macro raft agent of
example 2» part (b) and 10% amine modified poly(monoacryloxyethyl ate)w-block-
cry_lamide)m macro raft agent
Part (a): Preparation of stericaliy stabilized iron oxide nanoparticies from the aqueous
ferrofluid of example ‘1 part (a) and a 90:10 blend of the macro-RAFT agent of example 2
part (b) and the macro-RAFT agent ofexample 2 part (c).
Aqueous ferrofluid prepared according to example I, part (a) (8.10 g) was d with
MQ water (50 g) to yield a 0.5 wt% dispersion of the nanoparticles. The pH of this prepared
nanoparticle dispersion was then raised to S. A blend of RAFT which consist of 50 g of
at 6.3 wt% solids, 6.4 wt% of which was the macro-RAFT agent of e 2 part (b) and
05.9 wt% of which was the macro-RAFT agent of example 2 part (c) were mixed together and
the pH adjusted to 5 using 0.1M NaOH. The dESpersion of iron oxide. ined at the same
pH was then added to' the macro-RAFT blend. The mixture was vigorously stirred for 2 hours
at room temperature before the pH was ed to 7.0. The mixture was then left stirring for
another l2 hours. At this pH the copolymer remained partially neutralized while the
.nanoparticles were sufficiently above their point of zero charge to also be stable. The
dispersion was then dialysed to remove salts, residual solvents, unwanted low molecular
weight reaction side products and unbound polymer. The solid content of the dialysed aqueous
ferrofluid dispersion is 0.87%.
Part (b): Amine modification ofstabilisersfor iron oxide particles ofexample 22 part (a
into coated nanoparticles prepared from example 2 part (a) (60g). N-
hydroxysuccinimide (NHS, 24.7mg) and then l-Ethyl(3-Dimethylamino-
prepyl)carbodiimide (EDAC, 34mg) were added, mixed by shaking and allowed to react for 2
.68..
hours at room temperature. l8.2mg of 2,2‘-(Ethylenedioxy)br‘s—(ethylaminc) was then added to
the reaction mixture and allowed to react for a further i2 hours. The solution was then dialysed
against excess water with numerous changes, to remove free EDAC and the reaction by-
products.
EXAMPLE 23
Stabilisation of iron oxide nanoparticles with leuconostoc mesenteroides dextran (average
molecular weight 35,000-45,000 from sigma aldrich) (example 23 is a comparative .
example) .
ml of 0.5 M FeCl2/4H20 in solutions and 25ml of 1M FeCl3/6H20 in solution was
l0 magnetically stirred in a 500 ml 3 neck round bottom flask. The solution mixture was d
by adding 100 ml of Mili-Q water and the resulting on placed in an oil bath at 70°C.
After 10 minutes dextran solution (15%. 50 ml) was then added followed by ammonia
solution (28% 30 ml). The e was kept at 70°C for a further 45 minutes. The reaction
mixture was cooled to room ature and dialysed against MQ water to remove excess
l5 ammonia. The water was changed at least three times. Larger aggregates were d by
magnetic sedimentation. The volume of the dispersion was reduced to about lOO ml by using a
rotary evaporator. The final dispersion was sonicated at 70% AMFusing an ultrasoriicator for
l0 s followed by sonication at 30% AMP for 30 minute.
EXAMPLE 24
Steric stabilization of iron oxide rticles of example 1 part (3) using 98%
poly(monoacryloxyethyl phosphateho-block-polflethylene oxide)” macro raft agent and
2% amine modified poly(monoacryloxyethyl phosphate)m~hlock—poly(acrylamideho
macro raft agent
Part (a): Preparation of slerically stabilized iron oxide nanoparticles from the aqueous
ferrofluid of example 1 part (a) and a 98:2 blend of (he macro-RAFT agent of example 2
part (b) and the macro-RAFT agent ofexample 2 part (c). [EP341063]
Aqueous ‘luid prepared according to example 1, part (a) (8. 10 g) was diluted with
MQ} water (50 g) to yield a 0.5 wt% diSpersion of the nanoparticles. The pH of this ed
nanoparticle dispersion was then raised to 5. A blend of macro-RAFT which consist of 50 g of
at 6.48 wt% solids, 6.4 wt% of which was the macro-RAFT agent of example 2 part (b) and
0.08 wt% of which was the macro~RAFT agent of example 2 part (c) were mixed together and
the pH adjusted to 5 using 0.1M NaOH. The dispersion of iron oxide. maintained at the same
pH was then added to the macro-RAFT blend. The e was vigorously stirred for 2 hours
.69-
left stirring for
at room temperature before the pH was adjusted to 7.0. The mixture was then
another 12 hours: At this pH the copolymer remained partially neutralized while the
nanoPanicles were Sufficiently above their point of zero charge to also be stable. The
sion was then ed to remove salts. residual ts. ed low molecular
weight reaction side products and unbOUnd polymer. The solid content of the dialysed aqueous
uid dispersion is 0.8%.
Part (b): Amine modification ofstabilisers ofiron oxide particles of example 24 part (0)
Into coated nanoparticles prepared from example 24. Part (a) (55g), N-
ysuccinimide (NHS. 5.1 'mg) and then I -Ethyl(3—Dimethylamino-
propyl)carbodiimide (EDAC, 6.8 mg) were added, mixed by shakinglandallowed to react for 2
hours at room temperature. 2,2’-(Ethylenedioxy)bis-(ethylamine) (18.2 mg) was then added to
the reaction mixture, which was allowed to react for a further 12 hours. The solution was then
dialysed against excess water with numerous changes, to remove free EDAC and the reaction
by-products.
EXAMPLE 25
General method for preparation. of spheroids
Human DLD-l colon cancer cells and human PA-i ovarian cancer cells were obtained
from the American Type Culture Collection (Manassas, VA, USA). Cells were ined in
complete media (Advanced DMEM (lnvitrogen) and supplemented with 2% foetal bovine
Serum (Sigma) and 2mM axTM (lnvitrogen)) at 37°C in a humidified, 5% C02
atmosphere. Spheroids were formed by g lthlOs cells/ml onto agarose coated 96 well
imaging plates (BD Bioscicnces) and the cells allowed to aggregate for 72 hrs at 37°C in a
humidified, 5% C02 atmosphere resulting in the formation of single id per well.
EXAMPLE 26
Assessment of cytotoxicity of active compounds and nanoparticles
Active compounds and/or nanoparticles were diluted as required in cell media
immediately prior to the assay. Cytotoxicity was determined using the MTT assay. as follows. i
x 105 cells were seeded onto each well of flat bottomed 96-well plates and allowed to attach
overnight. Solutions of compounds +/- nanOparticles were added to triplicate wells at
concentrations spanning a 4—log range and incubated for 72 hrs. MTT (3»(4. 5-
dimethylthiazolyl~2)-2, S»diphenyltetrazoiium e) (1.0 mM) was added to each well and
were incubated for a further 4 hrs. The culture medium was removed from each well, DMSO
(150 uL) was added, the plate shaken for 5 seconds and the absorbance measured immediately
"at 600 nm in a Victor’V micrOplate reader (Perkin Elmer). {C50 values were determined as the
drug concentration that reduced the absorbance to 50% of that in untreated control wells. At
,least three independent experiments were performed for each compound with triplicate
readings in each experiment. Cytotoxicity values for all active compounds used are listed in
Table 2.
EXAMPLE 27
l method for treating the cancer spheroids of e 5 with (a) na'noparticles
alone, (b) inistration of nanopa rticles and active compound or (c) time course
ent of nanoparticle first then active compound
All nanoparticles were sterilised either by ion through a 0.22 pm filter or by
autoclaving at l20°C, 2 KPa for 20 min in a Tomy high pressure steam sterilizer ES-3l5
before use in cellular assays.
(a) To the suspension of the 3 day old spheroids from e 25, 100 pl of a solution
containing nanoparticles incomplete media was added to each spheroid, to yield a final
concentration of particles of lOppm- in 200 pl total volume. he spheroids were replaced in an
incubator at 37°C. 5% 002. After 24 hours incubation, the nanoparticles in the media were
removed by washing with excess ate buffered saline prior to further experimentation.
(b) To the suspension of the 3 day old spheroids from example 25, 100 pl of a solution
containing active compound and nanoparticles lete media was added to each spheroid,
to yield a ‘final concentration of particles of lOppm. The tration of the active
compounds used is defined in Table 3. The spheroids were replaced in an incubator 37°C. 5%
C02 atmosphere. After 24 hours incubation, the free active compound and nanoparticles in the
media were removed by washing with excess ate buffered saline.
(0) To the su5pension of the 3 day old spheroids from example 25, l00 pl of a solution
containing nanoparticles in complete media was added to each spheroid, to yield a final
concentration of particles of l0ppm. The spheroids were replaced in an incubator at 37°C, 5%
C02. After 24 hours incubation, the spheroids were closed with an active compound at the
concentration listed in Table 2 and incubated for a further 24 hours at 37°C, 5% C02. The free
3O active nd and nanOparticles in the media were removed by washing with excess
phosphate buffer saline prior to further mentation.
EXAMPLE 28
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.71.
General method for imaging spheroids treated with nanoparticles and a fluorescent
active compound by confocal microscopy.
Spheroids from example 25 were d as per example 27b and 27c then transferred
to a glass bottomed 35 mm dish (Mattek) and imaged on an Olympus FVIOOO confocal
micrOSCOpe using an Olympus UPLAPO [Ox/0.40 air objective lens. Single confocal images
h the central region of the Spheroid were taken. Excitation and on settings were
fluorophore dependent: Doxorubicin ex.:559nm em:575-675; ntrone ex:405nm, em2575-
EXAMPLE 29
General method for ing effectiveness of active compound +l- nanoparticles in
spheroids (outgrowth assay)
Spheroids from example 25 were treated as per example 27b and 27c. The spheroids
were then transferred to a 24 well plate using a wide bore transfer pipette and the medium
replaced with } mL of fresh media in each well. The spheroids were then incubated for 48
hours at 37°C in a 5% C02 humidified environment, allowing the spheroid to attach to the
plate and the cells to grow out from the spheroid onto the surface of the plate. Hoechst 33342
was then added to the wells and incubated for 30 minutes at 37°C in a 5% C02 humidified
environment. Widefield fluorescence images of the brightfield and Hoechst 33342 stained
nuclei were taken ofthe cells that had grown out from the spheroid (Olympus CellR)‘ To
quantitate the outgrowth, the number of nuclei within a 60° angle from the edge of the
id was counted. These values were then plotted in a graph ised to ids
treated with active compound alone or untreated control spheroids for comparison.
EXAMPLE 30
Sterically stabilised nanoparticles are able to penetrate into spheroids
ids from example 25 were treated asper e 27a with les from
example 2 and washed with phosphate buffered saline, followed by primary fixation with 2.5%
glutaraldehyde solutionand secondary fixation with 1% osmium tetroxide, The spheroids were
washed then dehydrated in a gradient of ethanol and infiltrated with Spurr’s Resin. Ultra-thin
sections with a nominal thickness of 95 nm were cut. placed on mesh grids and post stained
with uranyl acetate and lead e. TEM images of the spheroid sections were obtained using
a JEOL I400 TEM at 120 kV.
The images in Figure l were taken from the central regiOn ofthe id and show an
acoumulation of nanoparticles (darker stained areas as indicated with arrows) within the
cytoplasm of the cells. The enlarged region indicated by the box shows the well dispersed
individual'nanoparticles.
EXAMPLE 31
The effect of nanoparticles on drug diffusion
DLD-l spheroids prepared as were dosed the protocol in
per example 25 as per
example 27a with nanoparticles from es 2, 3, and _S) and imaged under ions
described in example 28. Dox0rubicin alone diffused approximately 70 um into the spheroid.
Co-administration of doxorubicin and NP3 or 5 enhanced the id penetration of
doxorubicin to approximately IOO pm. in contrast; co-administration ofNP2 and doxorubiein
resulted in doxorubiein diffusion throughout the entire spheroid (Figure 2A). Mitoxantrone
aloue also diffused approximately 70 um into the spheroid. Cooadministration of NP3 and
mitoxantrone had little effect on mitoxantrone diffusion, whereas co-administration of
mitoxantrone and NP2 or NPS significantly enhanced the diffusion of mitoxantrone into’ the
spheroid (Figure 23).
EXAMPLE 32
The effect of nanoparticles on spheroid viability
DLD—l spheroids ed as per example 25 were dosed as per the protocol in
e 27a with nanopaniclesfrom examples 1, 2, 4, 8, 9, l2, l3. 15, l6, and l8. The
effectiveness of nanoparticles alone in spheroids was assessed as per example 29. it was found
that the majority of nanoparticles tested had little cytotoxic effect as shown in Figure 3.
EXAMPLE 33
The effect of nanoparticies with different core types on the viability of spheroids
when co-administered with doxorubiein.
DLD-l spheroids prepared as per e 25 were dosed as per the protocol in
example 27b with nanoparticles from examples 2, 4, 6, 7, 9, 10, i1, 12, l3, I4, 16, 17, and
18 and doxorubicin. Effectiveness was determined as per e 29. Figure 4 shows that
inistration of nanoparticles‘NP2 (iron core), NPl 1(silica core), NPIZ (gold core),
and NP18 (polystyrene core) with doxombicin was more effective than doxorubicin
treatment alone as shown by the decreased cellular wth from the ids. The
composition of the nanopatticle core does not ate with effectiveness,
EXAMPLE 34
W0 2012/142669
s73.
when
The effect of nanoparticles with ent core sizes on the viability of spheroids
ninistered with doxorubicin.
DLD-l spheroids prepared as per example 25 were dosed as per the protocol in
example 27b with nanoparticles from examples I, 2, 4, 7f, 9, 10, ll, 12, l3, l4, l6, l7, and
18 and doxorubicin. Effectiveness was determined as per example 29. Several different
nanoparticles with a range of core sizes from 10 rim to 200nm when inistered with
doxorubicin were shown to be more effective than doxorubicin alone (Figure 5).It was
shown that co-administration of les NP]. NP2, NPIZ and NP! 8 co~administered with
doxorubicin was approximately 50% more effective than doxorubicin treatment alone.
‘ EXAMPLE 35
The effect of the functionalised stabiliser end group on spheroid viability when co-
administered with doxorubicin.
DLD-I ‘spheroids prepared as per e 25 were dosed as per the protocol in
example 27b with nanopanicles listed in examples 2, 3, 4, 5, 20, 21, 22, and 24 and
doxorubicin. Effectiveness was determined as per e 29. It was found thatthe
amine functionalised end group effected spheroid viability when co-administered with
doxorubicin. By varying the tage of amine functionalised groups on the surface of
the nanoparticles, we found that particles containing between 5-20% amine functionalised
end groups were the most effective when co—administered with doxorubicin. Doxorubicin
'
was the most ive when co-administered with nanopanicles containing stabilisers with
% amine onalised end groups.
EXAMPLE 36
Nanoparticles of different cores stabilised with 5% amine functionalised end groups
co-administered to spheroids with doxorubicin.
DLD~1 spheroids prepared as per example 25 were dosed as per the protocol in
example 271) with nanoparticles listed in examples 2, 8, 9 and 12 and doxorubicin.
Effectiveness was determined as per example 29. Nanoparticles stabilised with 5% amine
functionalised end groups were made with different cores and it was shown that all were
more effective than doxorubicin alone and had a similar'level of iveness when co-
3O administered with doxorubicin (Figure 7).
EXAMPLE 37
2012/000414
The effect of the active compounds when co-administered with nanOparticles on the
viability of spheroids made from two different cancer cell lines.
DLD~l and PA-l spheroids were prepared as per example 25 and dosed as per the _
protocol in example 271) with nanoparticles listed in examples 2. 3, 4, and 5 and active
cornpounds. Effectiveness was determined as per example 29. The majority of particles
and active compounds had similar effectiveness between the two cell lines, with the
exception of mitOXantrone. inistration of mitoxantrone and nanoparticles was
significantly more effective in the PA~l cell ovarian cancer cell line compared to the 01D-
1 colorectal cancer line.
EXAMPLE 38
Comparative example between co-administration of rticles and active
nds, and administration of rticles with delayed administration of.
active compounds in two different cell lines.
DLD-l and PA-l spheroids were prepared as per example 25 and closed as per the
protocol in example 27b and 270 with the rticles listed in examples 2. 3, 4, and 5
and active compounds. Effectiveness was determined as per example 29. Figures 9 and 10
show that for some le and active combinations e.g. 5FU+NP3 there is no difference
in effectiveness in either cell line for either mode of treatment. In general however, there
is little correlation n ent schedule and effectiveness n the two cell lines
tested. It will be important to determine which nanoparticle/active combination is most
effective for each cancer type. It should be noted that mitoxantrone requires the co-
administration of nanoparticles in PA-l cells for greatest effectiveness.
EXAMPLE 39
Examples of the most effective co-administered combination of rticlcs and ‘
active compound for each active compound tested.
DLD-l and PA-l spheroids were prepared as per example 25 and dosed as per the
protocol in example 27b with the nanoparticles listed in examples 2, 5, M, 20, 2}, and 22
and active compounds. Effectiveness was determined as per example 29. The results
presented are for the most effective nanoparticle(s) co-administered with each active
compound in both DLD-l spheroids (Figure HA) and PA-l spheroids (Figure 118).
EXAMPLE 40
Treating the cancer spheroids of example 25 with the iron oxide rticles of
es 1 and 2 to enable spheroid penetration by cisplatin.
DLD-l spheroids prepared as per example 25 were dosed as with 100 pl of solution
of complete media containing cisplatin and iron oxide nanoparticles from examples 1 and 2
to yield a final tration of both tin and iron oxide of 6ppm, The spheroids with
iron oxide particles and cisplatin were replaced in the tor and maintained at 37°C in
a 5% C02 atmosphere. After 48 hours incubation, the free cisplatin and nanoparticles in
the media were washed with excess phosphate buffered saline. Analysis by atomic
absorption spectroscopy showed that after 48 hours incubation the concentration of
ciSplatin in ”the spheroids with NP] nanoparticles, NPZ nanoparticles and without iron
oxide particles was 0.60, 0.63 and 020 ppb, respectively, a 3-fold increase in cisplatin
accumulation when nanoparticles were present.
E 4!
Comparative example: Doxorubicin penetration into spheroids when co-ad ministered
with anchored sterically'stabilised particles compared to co-administration with
unanchored sterically stabilised particles.
DLD-l spheroids from example 25 were either dosed with NP2 le 2), which are
particles coated with a stabiliser containing a ate anchoring group or NPl9 or NP23
les l9 and 23), which are particles coated with a stabiliser that has no anchoring
portion as per example 27b. The spheroid was then imaged by confocal micr05copy (as
per example 28) to visualise doxorubicin fluorescence. Spheroids treated with doxorubicin
and NH had significantly more doxorubicin fluorescence in the centre of the spheroid
compared to the spheroids treated with doxorubicin alone and to spheroids treated with
doxorubicin co—administered with the unanchored sterically-stabilised particles NPl9 and
NP23 (Figure :2).
EXAMPLE 42
Potential testing regime to determine the most effective nanoparticle and active
compound for patient tumours.
To identify which ) of nanoparticles and which ) of active drug and an
optimum combination of nanoparticles and drug were the most ive for an individual
patient, tumour biopsies would initially be tested. Several core tumour biopsies would be
~76 -
taken from a patient, dissected into smaller s (approx lmml) and closed with
selected nanopanicle/drug combinations. Each dosed sample would be flanked by an
untreated sample and a drug only to control for intra-tumour variability. After 24hrs= the
sample would be ted to an outgrowth assay to measure the efficacy of the tumour
treatments with nanoparticles/drug to determine the most ive compOSition and
administration of nanoparticles and drug:
Those skilled in the art will appreciate that the invention described herein is
susceptible to variations and modifications other than those specifically described, it is to
‘ be understood that the invention includes all such variations and modifications. The
invention also includes all of the steps, es, compositions and compounds referred to
or indicated in this cation, individually or collectively, and any and all combinations
of any two or more of said steps or features.
-77.
Table 1. LIST OF NANOPARTICLES USED TO EXEMPLIFY THIS PATENT
NP core, diameter
Fe203, IO-ISQm
F6203, 10-15nm
I Fc203,10-15nm
NP4 F6203, 10-1Snm
F6203, 10-15nm 100% NH;
2"Uas F6203, 10»15nm
m Fezol, 30.4mm
i"Uas 3:02, msnm
—-ssoz, m
“m 8102, I30nm 100% C00
u- 8102, 130nm 100% PEGAcr late
I—I N
Zw I- N Goid, 10—15nm 95%PEG 5%NH2
Gold, 3»8nm ’ 100% C00
NPI4 Gold, 10~15nm . 100% C00
NPIS Gold, m
E vs: ,~nsnm
Pst ,~4onm
PSI , ~200nm
F6203, 1045“!“
mo}, no-lsnm
F6203» 1045"?"
F8203, 10-15nm 90% PEG 10% NH:
Fe203, IO-ISnm 40K Dextran
Fe203, 10-15nm 98% PEG 2% NH;
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.73-~
Table 2: 72hr ICso values for the active compounds used in this study.
*Paclitaxcl was cytotoxic at concentrations as low as 0.] nM in this assay.
Table 3: Concentrations of active compounds used for dosin‘g in each cell line.
W0 2012/142669
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Claims (23)
1 . Use oftwo separate formulations of a particulate material and a in the manufacture ofa medicament for the to penetrate a solid tumour and induce xicity is in the form of a dispersion in a treatment ofa solid tumour n said particulate material the diSpersed state by a steric liquid carrier, the particulate material being maintained in and a steric stabilising stabiliser; wherein said steric stabiliser comprises an anchoring portion polymeric segment, wherein the anchoring portion is different from the steric ising towards the e of polymeric segment; and wherein the anchoring portion has an affinity material. the ulate material and secures the stabiliser to the particulate
2. The use according to claim 1, wherein the steric stabiliser has an average molecular weight of from about 1,000 to about 60,000 average molecular weight (Mn).
3. The use ing to claim 2, wherein the steric stabiliser has an average molecular weight ranging from about 1,000 to about 30,000 Mn.
4. The use according to claim 3, wherein the steric stabiliser has an average lar weight ranging from about 1,000 to about 5,000 Mn.
5. The use according to any one ofclaims 1 to 4, n the steric stabilising polymeric segment comprises a terminal ionic functional group.
6. The use according to claim 5, wherein the ionic onal group is a cation.
7. The use according to any one ofclaims 1 to 6, wherein the steric stabilising polymeric segment of the stabiliser comprises polymer selected from poly(acrylamide), thylene oxide), poly(hydroxyethylacrylate), poly(N—isopropylacry1a1nide), poly(dimethy1arninoethyl methacrylate), polyvinyl pyrrolidone), and copolymers thereof.
8. The use according to any one ms 1 to 7, wherein the steric stabilising polymeric segment has no more than about 50 polymerised monomer units that collectively form the H.\l'ml\[mcnruvcxuNRPanthCOFMNZbZ78L! docs~l7l09f2015 .8], segment.
9. The use according to any one of claims 1 to 8, wherein the anchoring portion one or more comprising one or more carboxylic acid groups, one or more phosphate groups, one or phosphinate groups, one or more thiol groups, one or more thiocarbonylthio , or combinations thereof. more sulfonic acid groups, ethoxysilyl ,
10. The use according to any one of claims 1 to 9, wherein one or both of the steric e of one or stabilising and ing polymeric ts comprise the polymerised more ethylenically unsaturated monomers.
11. The use ing to any one of claims 1 to 10, wherein the particulate material is selected from a metal, a metal alloy, a metal salt, a metal complex, a metal oxide, an inorganic oxide, a radioactive isotope, a polymer particle, and combinations thereof.
12. The use according to any one ofclaims 1 to 1 1, wherein the particulate material ranges in size from about IOnm to about 350nm.
13. The use according any one ofclaims 1 to 12, wherein said particulate material is iron.
14. The use according any one ofclaims 1 to 12, wherein said particulate material is gold.
15. The use according any one of claims 1 to 12, wherein said particulate al is siliCOn oxide.
16. The use according any one of claims 1 to 12, wherein said particulate material is yrene ranging in size from about lOnm to about 15nm.
17. The use according to any one of Claims 13 to 16, wherein said particulate material ranges in size from about 10 nm to about 15 nm.
18. The use according to Claim 15, wherein said particulate material ranges in size from H:\fnn\lnlcmot'anRPoflleCOFMT‘RZGZ73L] docs-I‘lltlv/mls , 32 _ about 30 nm to about 40 nm. material is co-
19. The use ing to any one ofClaims 1 to 18, wherein said particulate administered with from the one or more ar toxins ed group comprising: and/0r RNA interference herapy, targeted therapy, immunotherapy, radiotherapy therapy.
20. The use according to claim 19, wherein said chemotherapy is selected from actinomycin D, adriamycin, arsenic de, asparaginase, bleomycin, busulfan, camptosar, carboplatinum, carmustine, chlorambucil, cisplatin, corticosteroids, colicheamicin, cyclophosphamide, daunorubicin, docetaxel, doxorubicin, epirubicin, etoposide, fludarabine, fluorouracil, gemcitabina, gemcitabine, gemzar, hydroxyurea, idarubicin, ifosfamide, ecan, lomustine, lan, mercaptomurine, methotrexate, mitomycin, mitoxantrone, oxaliplatin, paclitaxel, platinol, platinex, procarbizine, raltitrexeel, rixin, steroids, streptozocin, taxol, taxotere, thioguanine, thiotepa, tomudex, topotecan, treosulfan, trihydrate, vinblastine, vincristine, vindesine, vinorelbina, vinorelbine, duanomycin, dactinomysin, esorubisin, mafosfamide, cytosine arabinoside, bis~chlor0ethylnitrosurea, mitomycin C, mitln'amycin, prednisone, hydroxyprogesterone, testosterone, tamoxifen, dacarbazine, hexamethylmelamine, pentamethylmelamine, amsacrine, chlorambudil,, methylcyclohexylnitrosurea, nitrogen mustards, cyclophosphamide, aptopurine, 6~thioguanine, cytarabine, S—azacytidine, deoxyco-formycin, 4-hydroxyperoxycyclophosphoramide, S-fiuorouracil (S-FU), S-fluorodeoxyuridine (S-FUdR), cine, trimetrexate, teni-poside, and lstilbestrol.
21. The use according to claim 20, wherein said chemotherapy is selected from the group comprising doxorubicin, mitoxantrone, cisplatin, paclitaxel and S-FU.
22. The use according to claim 19, wherein said RNA erence therapy is an RNA oligonucleotide.
23. The use according to any one of claims 1 to 22, wherein said particulate material or steric stabiliser r comprises a ligand directed to said solid tumour. Ht\fuu\lmumor:u\NRPunbl\DCC\FMm2627XZ_ | .docx-
Applications Claiming Priority (7)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US201161477382P | 2011-04-20 | 2011-04-20 | |
AU2011901495 | 2011-04-20 | ||
US61/477,382 | 2011-04-20 | ||
AU2011901495A AU2011901495A0 (en) | 2011-04-20 | A method of treatment and agents useful for same | |
AU2012900480A AU2012900480A0 (en) | 2012-02-09 | A method of treatment and agents useful for same | |
AU2012900480 | 2012-02-09 | ||
PCT/AU2012/000414 WO2012142669A1 (en) | 2011-04-20 | 2012-04-20 | A method for the treatment of a solid tumour |
Publications (2)
Publication Number | Publication Date |
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NZ616780A NZ616780A (en) | 2015-10-30 |
NZ616780B2 true NZ616780B2 (en) | 2016-02-02 |
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