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Provided by the author(s) and NUI Galway in accordance with publisher policies. Please cite the published
version when available.
Downloaded 2022-07-19T00:35:21Z
Some rights reserved. For more information, please see the item record link above.
TitleAn injectable collagen scaffold delivering exogenousmicroRNA as a therapy to modulate extracellular matrixremodelling
An Injectable Collagen Scaffold Delivering Exogenous microRNA as a Therapy to Modulate
Extracellular Matrix Remodelling
A thesis submitted to the National University of Ireland for the
Degree of Doctor of Philosophy
By
Michael Monaghan
April 2013
Network of Excellence for Functional Biomaterials
National University of Ireland, Galway
Research Supervisor: Professor Abhay Pandit
ii
iii
Table of Contents
List of Appendices ........................................................................................................................................ vii
List of Figures ................................................................................................................................................. x
List of Tables ............................................................................................................................................... xix
Acknowledgements ...................................................................................................................................... xxi
List of Abbreviations .................................................................................................................................. xxii
C. Materials and Reagents ......................................................................................................................... 230
D. Re-Constitution of Collagen .................................................................................................................. 234
D.1. Sircol Assay to Determine Collagen Purity .................................................................................. 234
D.2. Preparation of Non-crosslinked Hydrogel ..................................................................................... 235
D.3. Crosslinking of Collagen Type I Hydrogel using 4S-Succinimydyl Glutarate Terminated Poly
G.8. Gigaprep™ Protocol for Extraction of Plasmid DNA ..................................................................... 245
G.9. Sequencing of Constructed Plasmid DNA
H. In Vitro Transfection ............................................................................................................................. 247
H.1. Gaussia Transfection of Cultured Cells......................................................................................... 247
I. Cell Culture ............................................................................................................................................ 249
L.2. Immunostaining of Transfer Membrane from Western Blot .......................................................... 265
M. Protein Blot Array ................................................................................................................................ 266
M.1. Protein Extraction ........................................................................................................................ 266
M.2. Protein Blot ................................................................................................................................. 267
M.3. Image Analysis (Using LUTS Protein Membrane Array ............................................................... 268
ix
N. Michael –type Addition of Fab`s to Hyperbranched Polymer ........................................................... 270
N.1. Ellman’s Assay for Quantitation of Reduced Fragments Material Preparation ............................... 270
N.2. Michael-type Addition Conjugation of Antibody Fragments to pDMAEMA co-branched
O. Rat Excisional Model ............................................................................................................................. 271
P. Generation of In Vitro Human Skin Equivalents .................................................................................. 275
P.1. Isolation of Keratinocytes ............................................................................................................ 275
P.2. Isolation of Fibroblasts................................................................................................................. 276
P.3. Generation of Organotypical Skin Model ..................................................................................... 276
Q.1. Formalin Fixation for Tissue ........................................................................................................ 279
Q.2. Fixation with 4 % Paraformaldehyde in PBS: for Cells ................................................................. 279
R. Staining Methods ................................................................................................................................... 278
R.1. Haematoxylin and Eosin Staining ................................................................................................ 278
R.2. Russell Movat Pentachrome Stain ................................................................................................ 279
S. RNA Extraction ...................................................................................................................................... 286
S.1. Extraction from Cells and Scaffolds ............................................................................................. 286
T. Reverse Transcription of RNA to cDNA ............................................................................................... 287
T.1. Reverse Transcription of RNA to cDNA for Regular PCR ............................................................ 287
T.2. Reverse Transcription of RNA to cDNA for RT2 Profiler PCR Array ........................................... 289
U. Real-time PCR ....................................................................................................................................... 289
STAT3 Signal Transducer and Activator of Transcription 3
TAT Tyrosine Aminotransferase
TBE Tris-Borate
Tfr Transferrin Receptor
xxv
TGF-β Transforming Growth Factor beta
TIPA Radio Immunoprecipitation Assay
TLR Toll-Like Receptors
TNBSA 2,2,6-Trinitrobenzenesulfonic Acid
TNF-α Tissue Necrosis Factor alpha
TR Transferrin
TRBP TAR RNA Binding Protein
UTR Untranslated Region
UV Ultraviolet
v/v Volume per Volume
VCAM Vascular Cell Adhesion Molecule
VEGF Vascular Endothelial Growth Factor
VEGFR Vascular Endothelial Growth Factor Receptor
Vif Virion Infectivity Factor
VS Vinyl-Sufone
w/v Weight per Volume
w/w Weight to Weight Ratio
xxvi
Abstract
Cardiovascular disease is the leading cause of death in the developed world and is responsible for
approximately 36% of Irish mortality. Myocardial infarction (MI), which is literally the death of
cardiac tissue due to lack of oxygenation, accounts for the majority of deaths associated with
cardiovascular disease. This death of cardiac tissue leads to a loss of cardiac function as the damaged
area becomes a non-contractile scar. Amelioration of this process is a main aim of regenerative
cardiac strategies such as anti-fibrotic therapies. Thus, anti-fibrotic interfering RNA (RNAi) therapy
with exogenous microRNA (miR)-29B was proposed as a method to modulate extracellular matrix
(ECM) remodelling following MI. It was hypothesized that miR-29B scaffold delivery will efficiently
modulate the ECM remodelling response and reduce maladaptive remodelling, such as aggressive
deposition of collagen type I, after injury. The primary objective of this doctoral project was to
develop a scaffold-based, controlled release gene therapy system. A co-polymer of a linear poly
(dimethylamino) ethyl methacrylate (pDMAEMA) block and a hyperbranched poly (ethylene glycol)
methyl ether acrylate (PEGMEA) based unit with poly (ethylene glycol) diacrylate (PEGDA) as the
branching agent (pD-b-/PDA) was synthesised, with the purpose of complexing miRs, using
deactivation enhanced atom transfer radical (De-ATRP) synthesis. Non-viral complexes of miR-29B
and pD-b-/PDA were optimized for both monolayer and three-dimensional delivery from a crosslinked
collagen-based scaffold in vitro. The release of these complexes from the scaffolds was assessed and
their ability to silence collagen type I and collagen type III expression was evaluated. When cardiac
fibroblasts were cultured with complex loaded scaffolds, relatively low levels of collagen type I and
collagen type III mRNA expression were observed for up to two weeks of culture. When scaffolds
loaded with miR-29B or miR-29B complexes were applied to a rat excisional wound model, reduced
wound contraction, improved collagen type III/I ratios and a significantly higher MMP-8: TIMP-1
ratio were detected. From these investigations it was concluded miR-29B functionalization of the
scaffold significantly increased the ratio of collagen type III/I and MMP-8/TIMP-1 ratios.
Furthermore, these effects were not improved through the use of pD-b-/PDA, and were significantly
influenced by the dose of miR-29B in the collagen scaffold (0.5 μg versus 5 μg). This is the first study
to describe a biomaterial scaffold combined exogenous miRs capable of improving ECM remodelling
following injury. There is significant potential for further development of this platform which could
ultimately represent a step towards the realization of true cardiac regeneration.
Chapter One
Literature Review
The majority of this chapter has been previously published in
Monaghan M, Pandit A. RNA interference therapy via functionalized scaffolds. Adv. Drug Del. Rev. 2011, 63: 197-208
Monaghan M, Greiser U, Wall J.G, O'Brien T, Pandit A. Interference: An alteRNAtive therapy following acute myocardial infarction. Trends Pharmacol. Sci. 2012, 33: 635-645
Literature Review
2
1.1 Introduction
Tissue engineering is the use of a combination of biomaterial scaffolds, cells, and engineering, with
suitable biochemical and physio-chemical factors to improve or replace biological functions 1.
Scaffolds employed in tissue engineering act as platforms that can recapitulate the in vivo milieu,
allowing cells to influence their own microenvironments and/or retain cells and biochemical factors.
These scaffolds can provide structural support, porosity to enable cellular infiltration, and possible
release of embedded biomolecules and cues for the surrounding tissues to regenerate. Scaffolds can be
further ameliorated by the incorporation of cells to replace those that have been lost or to offer
paracrine support to those that are compromised at the site of delivery 2. Biomaterial-based scaffolds
have played a central role in regenerative medicine and tissue engineering and several key
requirements for scaffolds have been identified. Scaffolds fabricated from a range of natural and
synthetic materials are desired to be biodegradable to obviate the need for a removal procedure. In
tandem, predictable biodegradation of the scaffold can facilitate controlled release of biomolecules
embedded within the scaffold. The degradation time of the scaffold should ideally mirror the time
necessary for tissue regeneration. Degradation of the biomaterial can create a path for tissue ingrowth
and this can be further facilitated by a highly porous scaffold which can also allow for the initial
transport of oxygen and nutrients, as well as for the removal of metabolic waste and degradation
products.
The current paradigm of tissue engineering incorporates the use of biomolecules, which can be growth
factors, pharmaceutical agents, or mediators of nucleic acid therapy. Therefore it is intuitive that
scaffolds act as reservoirs in the delivery of nucleic acid such as interfering RNA (RNAi) (see Figure
1.2). RNAi delivery from a scaffold enables localized treatment, as the scaffold, acting as a reservoir
of RNAi, facilitates delivery of this therapeutic molecule in comparison to delivery via a systemic
approach 3, 4
. Targeting a cell population or anatomical location by injection or systemic delivery is
complex and poses many challenges; direct delivery of a therapy from a scaffold, however, can
surmount these barriers. Cells surrounding a scaffold are considered for targeting and become
exposed to the therapeutic agent limiting unwanted exposure in other areas. Additionally, scaffold-
based delivery has the potential to maintain effective levels of payload and nucleotide bioactivity for
extended periods which broadens the opportunity for cellular uptake and increases the likelihood of
nucleic acid transfer. Delivery from the majority of biomaterial systems most likely occurs by means
of a combination of payload interaction with the matrix and subsequent release, with the payload and
material designed to regulate these interactions.
Literature Review
3
Another advantage of a scaffold is its role in the protection of its payload from attack by immune
responses, and limitation of degradation by serum nucleases or proteases. The use of scaffolds in the
delivery of nucleic acid therapy has been extensively reviewed previously 4, 5
; and the basic criteria,
concepts and interactions between scaffolds and their therapeutic loads do not change in the context of
RNAi delivery.
1.2 RNA Interference
RNAi is a fundamental pathway in eukaryotic cells by which sequence-specific double stranded RNA
targets, binds to, and inhibits the translation of a complementary mRNA. Many similar RNAi
mechanisms exist which pursue distinct pathways inside eukaryotic cells. In general, however, most
pathways terminate at a common end; in that they inhibit the translation of messenger RNA (mRNA)
(see Figure 1.1). Synthetic approaches employing antisense oligonucleotides have evolved to double
stranded RNAs (dsRNAs) following seminal discoveries by Fire et al. in 2001 6, illustrating a ten-fold
improvement in silencing target genes when compared to a single stranded RNA alone. These
exogenous molecules manipulate an existing regulatory pathway: that of microRNA (miR).
The miR pathway begins in the nucleus with transcription of long primary miR (pri-miRs) by RNA
polymerase II (Pol II) 7 and subsequent processing into ~70 nucleotide (nt) stem-loop structures
termed ‗precursor miRAs‘ (pre—miRs) by the RNase III enzyme Drosha which functions with the
dsRNA binding protein of DiGeorge syndrome critical region 8 (DGCR8) 8. Exportin-5, another
dsRNA- binding protein, chaperones these pre-miRs to the cytoplasm in a Ran-GTP-dependent
manner. Once in the cytoplasm; Dicer, an endoribonuclease in the RNAse III family, and its
associated dsRNA-binding protein partners, HIV-1 and the TAR RNA binding protein (TRBP) 9,
cleave pre-miR to a mature miR duplex ~22 nt long and load this mature miR into a RNA induced
silencing complex (RISC) 10, 11
. miR interaction with RISC involves cleavage of the miR passenger
strand by Ago2 although imperfect sequence complementarities between the mature miR strand and
its complementary passenger strand may inhibit Ago2 from cleaving the passenger strand 12
.
Alternatively, this interface employs a circumventing mechanism using helicase activity to unwind
and remove the passenger strand. Regardless of the mechanism, the removal of passenger strand
enables the binding of the mature miR to its target mRNA 3‘ UTR. Gene silencing is then catalysed
by RISC through translational repression and consequent mRNA degradation.
The seed sequence of a mature miR encompasses the first 2 - 7 or 2 - 2 nucleotides from its 5‘ end and
needs to have full complementarity with its target to enable RNAi, whereas imperfect matches in the
3‘ end of the miR strand are tolerable 13
. As a result, a single miR can regulate multiple cellular
Literature Review
4
targets and, conversely, each gene can be controlled by many miRs, suggesting an elaborate and
multifaceted mechanism of gene regulation. Numerous hypotheses toward the effects of imperfect
binding of a miR to its target mRNA and its effect on gene silencing have been put forward, including
interruption of translation at the initiation or elongation step, co-translational degradation,
transportation to cytoplasmic processing bodies (P-bodies), and/or de-capping or deadenylation 14-16
.
On the other hand, when complete sequence complementarities occur; silencing is achieved via
cleavage of the mRNA through RISC activity 17
. In both cases, miR targeting and binding results in
post-transcriptional silencing of the target gene.
Appreciation of endogenous RNAi pathways has enabled improvement in synthetic strategies to
silence gene expression. One approach is to, albeit stably or transiently using plasmid DNA (pDNA)
encoding the expression of short hairpin RNA (shRNA) 18-20
or delivery to the cytosol of
shRNA/siRNA and dsRNA. The utilization of either approach needs to account for the stability, the
therapeutic target and the efficacy of delivery. Efficacy of shRNA-expressing pDNA requires entry
into the cell, endosomal escape and subsequent entry to the nucleus via a nuclear pore, as in the case
of non-dividing cells 21, 22
or nuclear uptake during cell division 23
. An alternative approach is to
deliver dsRNAs exogenously which become cleaved in the cytoplasm by Drosha to siRNA and
subsequently loaded into the Argonaut/RISC complex. Therefore, dsRNAs are advantageous in
delivery compared with shRNA-expressing pDNA as they obviate the necessity for nuclear entry and
can therefore enable a more efficient process of RNAi. Silencing gene expression using long dsRNAs
has been demonstrated in an array of organisms including plants and drosophila. However, in
mammalian cells, it has been observed that dsRNAs longer than ~30 nt elicit an antiviral associated
interferon response which ultimately results in non-specific suppression of gene expression through
activation of RNase L and general degradation of RNA molecules 24
.
This response can be evaded however, by the design of the dsRNA. Elbashir et al. observed that
smaller dsRNAs, less than 30 nt are capable of bypassing the mammalian immune response while
inducing RNA interference to achieve specific gene silencing 25
. This realisation progressed to the
hypothesis that synthetic dsRNAs of very short length (siRNAs) with perfect homology to the mRNA
of a target gene can be delivered as an alternative mediator of gene silencing. However, early innate
immuno-stimulatory activity with these synthetic molecules remains a concern. siRNAs containing
certain nucleotide sequence motifs (GU) can stimulate toll-like receptors (TLRs) in the endosomal
pathway. Obviation of this is desirable because if it is not carefully avoided, siRNAs capable of
triggering immuno-stimulatory activity 26
. The antigenic potential of siRNAs can occur via TLR-3,
and has been reported as a possible safety concern 27
. This has brought scrutiny to some studies where
anti-angiogenic specific siRNAs have been reported as being successful as other pre-clinical studies
Literature Review
5
have concluded that non-specific siRNAs also induce an anti-angiogenic effect due to interaction with
TLRs, and engaging the TLR3/interleukin pathway 28
.
The exogenous introduction of short siRNAs with appropriate length and 2-nt 3‘ overhang can be
loaded directly onto RISC for RNAi function, obviating interaction with Dicer, TRBP or protein
kinase RNA activator (PACT); however, the loading process is ten times less efficient than that of
shRNA or longer dsRNAs. Increasing the length of the siRNA duplex to 29-30 nt with a 2-nt 3‘
overhang only at the antisense end of the duplex appears to improve efficacy 29
. Dicer processing
before RISC loading can increase the potency of post-transcriptional gene silencing and can be
achieved by using longer chemically synthesized siRNAs (27 nt) and shRNAs (28 nt) 29, 30
. It is likely
that Dicer and TRBP-PACT present an effective basis for RISC formation and shuttle their cleaved
products directly to RISC 12, 31
. Employing this loading stem in exogenous RNAi therapies can elicit a
more potent gene-silencing effect through the use of these Dicer substrates. Twenty seven nt dsRNAs
are intended to be asymmetrical, with one 2-nt 3‘ overhang and one blunt end. A single stranded
siRNA results from Dicer processing due to Dicer recognition of the 2-nt 3‘ overhang for processing.
However, the blunt end, which includes DNA bases, might trigger low levels of interferon induction;
but the potency of this longer dsRNA means that lower concentrations of 27 mers are required to
silence gene expression which may avoid or minimise such an interferon response 32
. Furthermore, it
is possible that increasing the length of a siRNA duplex with an unprocessed end dictates
directionality as a result of imposed thermodynamic instability determining the guide strand shape and
thereby enhancing its association with Dicer/TRBP/PACT complex for more efficient loading onto
RISC. shRNA on the other hand, assimilates into the endogenous miR pathway and in doing so is
significantly more efficient 33, 34
.
1.3 Non-viral Delivery
Current clinical applications of RNAi are focused on using previously mentioned 21–nt siRNA
duplexes with 2-nt 3‘ overhangs for Dicer recognition which are suitable for large-scale synthesis that
enables uniform production of these chemically synthesized molecules. The clinical relevance of
siRNA is supported by its ability to transfect relatively non-proliferating cells in which the nuclear
entry of shRNA-expressing pDNA is limited. For example, successful target gene knockdown in cells
such as bone marrow-derived dendritic cells 35
and primary T lymphocytes 36
, for which transfection
with pDNA is difficult due to low permeability in their nuclear envelope has been reported with
siRNA. For a quantitative comparison of the duration of effect of siRNA and shRNA-expressing
pDNA, McAnuff et al. compared the potency of siRNA and shRNA-expressing pDNA mediated
gene-silencing in vivo by co-administration of siRNA or shRNA-expressing pDNA with the pDNA
Literature Review
6
Figure 1.1: Schematic illustrating non-viral RNAi delivery mechanisms. Red arrows show the
mechanism of siRNA and miR mimics entering the cell, uptake and activation by RISC, binding
to target mRNA and inhibiting translation. Blue arrows indicate the delivery of pDNA encoding
shRNA, which must enter the nucleus to transcribe shRNA from the nucleus. shRNA becomes
cleaved by DICER, uploaded by RISC and terminates at the same endpoint as the red arrow
pathway. Finally, black arrows indicate the delivery of antagomiRs, designed to bind to
endogenous miRs and inhibit them from binding to their target mRNAs *.
* Adapted from Monaghan M, Pandit A. RNA interference therapy via functionalized scaffolds. Adv. Drug Del. Rev. 2011, 63: 197-208
Literature Review
7
encoding a target reporter gene 33
. The extent of the reduction in the target gene expression was
comparable to that between siRNA and shRNA-expressing pDNA at a 10 mg dose; however on a
molar basis, the shRNA was 250 fold more effective than the siRNA, at day one and day three after
administration. A concern in this study was that the expression of the reporter gene was transient, and
therefore it was difficult to conclude whether these compounds were effective and, furthermore, were
comparable with each other for longer than three days. pDNA transient transfection of cells in vitro
exhibits gene silencing at day three and day five in rapidly dividing cell lines and using naked siRNAs
achieves transient gene knockdown for at day three and day seven due to dilution of the siRNAs
below a therapeutic level with repeated cell division. In quiescent or non-dividing cells, the silencing
effect can remain at three weeks 37
after which the siRNAs are hypothesized to have been naturally
degraded. In vivo, a similar trend was observed using rapidly dividing subcutaneous tumours vs. non-
dividing hepatocytes.
A significant hindrance to the progression of siRNA therapies is delivery of these biomolecules to the
desired cell type, tissue or organ, because their negative charge and size prevents passive endocytosis
across the cellular membrane. Furthermore, their progress has been obstructed due to their rapid
clearance and lack of target tissue specificity. It is evident from the plethora of research reported on
the delivery of gene encoding pDNA by non-viral methods; overlapping and additional considerations
are required when introducing synthetic RNAs or RNA encoding plasmid DNA to eukaryotic cells.
Plasmid DNA is often several kilo base pairs long, and possesses molecular characteristics that allow
it to be condensed into particles, from submicron up to just a few microns in size, by complexation
with a cationic agent. This condensation is driven for the most part by electrostatic attraction and
ensures that pDNA is protected against enzymatic degradation as it becomes entirely encapsulated by
the cationic agent. Furthermore, the condensing of large pDNA constructs enables a favourable size
for cellular uptake via the endosomal pathway 38
. However, RNA and DNA are different types of
nucleic structures and their physico-chemical properties are determinants of their ability to complex.
The persistence length of siRNA and pDNA is an important consideration in the delivery of these
molecules. This is the length over which chains of nucleic acid base pairs act as individual rigid
elements. dsDNA has a persistence length of about 50 nm, whereas dsRNA is ~70 nm which lends
RNA to be a stiffer molecule 39, 40
. Translating this to a nucleotide (nt) scale, the persistence length of
RNA is about 260 nt. This suggests that a 21 nt siRNA does not condense further and, that when
improperly fractioned with cationic agents, will form inefficient large complexes or insufficient
encapsulation of the siRNA. The maximum size for clatherin mediated cellular uptake is 150 nm, and
particles larger than this do not diffuse passively across the cell membrane 38, 41
. In fact, with respect
Literature Review
8
to siRNA complexes, it has been shown 42
that particles of siRNA complexed with poly(ethylenimine)
(PEI) greater than 150 nm in size are unable to cause gene silencing in vitro.
RNAi can be therapeutically viable with the use of a non-viral vector by prolonging the serum half-
life and intracellular buffering of siRNA by improving pharmacokinetics and nuclease resistance. For
example, it has been reported that chemically modified siRNAs encapsulated within a lipid core have
extended serum half-life (6.5h) compared to those without protection (0.8h). Non-viral vectors
available for siRNA/pDNA delivery, such as cationic polymers 43
, lipid based approaches 44
,
nanoparticle approaches or biomolecular chaperoning as these areas have been covered in exhaustive
reviews 45, 46
; and key developments in pre-clinical and clinical studies will be elaborated in the next
section.
1.4 RNAi as a Therapeutic
The use of RNAi has undergone a rapid transition to pre-clinical studies due to advances made
previously in non-viral nucleic acid delivery and the current understanding of cellular pathways
during states of pathogenesis, and due to the availability of a wide range of in vivo models. Although
clinical trials are in progress, the number of these trials is relatively few and almost all of these trials
employ naked or slightly modified siRNAs to deliver RNAi.
The most advanced clinical trials are in the treatment of age-related macular degeneration (AMD)
which is a leading cause of blindness. These trials involve the injection of naked siRNA into the
macula of the eye, targeted to genes for vascular endothelial growth factor (VEGF-A) and the VEGF
receptor (VEGFR), and have shown some therapeutic potential in their inhibition of excessive
vascularization of the eye that leads to AMD 47
. The first clinical trial involving siRNA was carried
out by Acuity Pharmaceuticals Inc. for the treatment of AMD, for which phase I results have been
completed. The completed phase II trials reported tolerated doses with a lack of adverse systemic
effects. Testing had advanced into phase III trials, when Acuity Pharmaceuticals Inc. was taken over
by OPKO Health Inc.; however, the company decided to terminate its phase III clinical study of
bevasiranib (a naked siRNA) for the treatment of AMD. No systemic safety issues were identified and
local ocular risks were generally considered ‗unremarkable‘ by the company. However, a careful
review of the data by the Independent Data Monitoring Committee (IDMC) concluded that the trial,
as structured, was unlikely to meet a significant beneficial primary end point 48
.
Allergen Inc. is conducting a phase II clinical trial on a siRNA therapy for AMD, with completed
phase I results indicating minimal side effects and improved vision in some of the patients 49
. In the
phase I clinical trial targeting VEGFR-1 in patients with choroidal neovascularisation resulting from
Literature Review
9
AMD; mild to moderate adverse effects and an adjusted mean foveal thickness within two weeks after
the study treatment was reported. However, the trial co-ordinators, Allergen Inc., halted development
of AGN211745, a chemically modified siRNA, after the drug failed to meet a key efficacy endpoint in
a phase II study 50
. No safety issues were associated with AGN211745 targeting VEGF-1; but as the
drug did ‗not meet its efficacy hurdle‘, its development was halted. Silence Therapeutics Plc. also had
a siRNA product to treat AMD in development, but have now refocused their phase II clinical study
toward the treatment of diabetic macular edema, which is another complication caused by leaky
vasculature within the eye 51
.
The anti-angiogenic effect reported in AMD clinical trials has been called into question by a study
conducted by Kleinman et al.28
. Here, the authors reported that the efficiency of siRNA targeting
VEGF in the eye, in patients with choroidal neovascularisaton resulting from AMD, is not due to
specific gene silencing, but is instead caused by non-specific stimulation of the TLR-3 pathway which
can reduce angiogenesis 28
. This raises concern over the nature of the anti-angiogenic effects reported
in other AMD clinical trials; however, it should not compromise therapeutic effects described when
other mechanisms (unrelated to angiogenesis) are targeted. Clinical evidence for the effectiveness of
RNAi as a therapeutic approach for AMD is questionable; however there are some recent publications
showing promising results in addressing other therapeutic targets which are summarized in Table 1.1
52-66.
For instance, in a recent phase II randomized, double-blind placebo-controlled study of ALN-TSV01,
a siRNA directed against mRNA of the respiratory syncytial virus (RSV) nucleocapsid (NP) protein
was administered daily via a nasal spray 52
to subjects two days before and three days after
inoculation with RSV. It was reported that independent of other factors, including pre-existing
immunity to the virus or secondary inflammation, the RSV-NP siRNA resulted in a 38% decrease in
the number of culture-defined RSV infected patients.
Progress of a phase I clinical trial in systemically delivering targeted siRNA nanoparticles toward
metastatic melanoma have been documented by Davis et al .53
. This platform consisted of a
cyclodextrin-based polymer (CDP) particle, loaded with a siRNA for silencing expression of RRM2,
decorated with PEG to improve stability for systemic delivery, with a human transferrin protein (Tf)
targeting ligand displayed on the exterior to engage TF receptors on the surface of cancer cells.
Tumour biopsies showed localized presence of nanoparticles delivered systemically, and furthermore,
a reduction was found in both the specific mRNA and RRM2 protein levels when compared with pre-
dosing tissue. This is the first study that illustrated the localization of systemically delivered
nanoparticles and, furthermore, is the first clinical trial to use a biomaterial approach in the delivery of
Literature Review
10
Table 1.1: Selected examples of pre-clinical studies with non-viral delivery of siRNAs
Mode of delivery Application/disease Target Observations Reference
Lipid/Liposomal
Liposomal (i-FECT™)
Japanese encephalitis virus, West Nile virus
Viral envelope gene
Protection against both viruses when administered
54
Lipofectamine™ Ocular neovascularisation
VEGF-A Severity of neoangiogenesis was reduced
55
Lipofectamine 2000™ in Agarose matrix
Wound healing Mapk-1 and lamin A/C
Target proteins, and their gene expression were silenced at days 14 and 21(Mapk-1 and lamin A/C)
56
LipoTrust™ Liver cirrhosis Gp46 Liver fibrosis was reversed in experimental models
57
PEGylated cationic lipid particles
Ovarian cancer Claudin-3
Reduced tumour size and tumor burden when siRNA silencing claudin-3 was administered
58
Lipofectamine 2000™
Hepatitis C GB virus-B Dose dependent repression was achieved
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Chapter Two
Delivering Exogenous miRNA
The majority of this chapter has been previously published in:
Monaghan M, Greiser U, Cao H, Wang W, Pandit A. An antibody fragment functionalized dendritic pegylated poly(2-(dimethylamino)ethyl diacrylate) as a vehicle of exogenous microRNA. Drug Deliv. Trans. Res. 2012;2:406-414
Delivering Exogenous miRNA
60
2.1 Introduction
RNA interference (RNAi) is recognized as another gene therapy in manipulating the proteomic
behaviour of cells and tissues at the post-transcriptional level. There is significant interest in the
manipulation of endogenous small interfering microRNAs (miRs) and their subsequent increase
and/or decrease in levels in states of development, regeneration, remodelling and pathogenesis 1-4
.
These small, non-coding, naturally occurring RNAs negatively regulate the stability and
translation of target protein-coding mRNAs at the 3` untranslated region. They typically affect a
cluster of genes rather than one specific gene, and this allows them to play critical roles in a
variety of biological processes.
Intuitively, delivery of such a therapeutic is a criterion that needs to be addressed as miRs are
highly prone to degradation by ubiquitous RNases, have a short half-life in serum, must be
internalized into eukaryotic cells and require obviation of lysosomal compartmentalisation.
Additionally, they must reach their intended target effectively and persist for an extended of time
as in the case of systemic delivery 5. The delivery of exogenous miRs, similar to plasmid based
gene therapy, is achievable through both a viral and non-viral approach. Viral delivery systems
exist have been tested in clinical studies to date, to effect long-term expression of a therapeutic
gene with excellent efficiency, but sometimes transient regulation of aberrant genes during acute
illnesses may be desired. Viral delivery also has inherent safety concerns such as immunogenicity
and possible mutation; and despite advances in the field to overcome these concerns 6, these
factors still remain contentious. A non-viral vector approach, although less efficient than viral
vectors, offers transient, and sometimes stable expression, is better suited to the mass production
and the scalability necessary for clinical translation 7. Non-viral vectors can prolong the serum
half-life and intracellular buffering of the nucleic acid cargo, thereby improving pharmacokinetics
and nuclease resistance. Previously, exogenous miRs have been complexed (encapsulated via
electrostatic interactions between a cationic polymer and the negatively charged nucleic acid) and
delivered using copolypeptides 8. More recently, studies have reported on the therapeutic effect of
delivering non-viral miRs in the form of duplex mature miR sequences using liposomal based
carriers 9 and plasmid DNA (pDNA) transcribing candidate miRs delivered systemically using
liposomes 10
. As with the delivery of exogenous DNA to cells, efforts are being made to deliver
interfering RNA by a number of non-viral methods which include liposomes 11
, nanoparticles 12
and cationic polymers 13
. Specifically, the use of cationic polymer structures offers a facile
approach that can enable tuneable, efficient and potentially large-scale production to be achieved.
Delivering Exogenous miRNA
61
To complex miR with a cationic polymer, a charge interaction transpires with that of the
negatively charged phosphate groups of nucleic acid, usually facilitated by tertiary or secondary
amines of the complexing agent. Efforts at reducing the toxicity of these polymers include
PEGylation to enable systemic delivery and adequate interaction with blood components (thereby
increasing circulation times) and the decoration of these structures with peptide and/or protein
sequences. However, both these approaches present limitations in both processing and in the
efficacy of the carrier. PEGylation of carriers does improve serum interaction and reduces toxicity
with cells. Their functionalisation with peptides or monoclonal antibodies can introduce issues of
immunogenicity and requires secondary linking which can be cumbersome and often introduces
hazardous compounds 14
.
The use of Michael-type addition reaction offers a facile „click chemistry‟ approach in which an
alkaline reaction solution behaves as a base donor and can enable covalent linkage, most
commonly between vinyl groups and thiol (SH) moieties. Previous approaches have employed
this technique in decorating surfaces with SH functionalized peptides with effective outcomes 15
.
This reaction enables a facile and orientated conjugation of SH terminated antibody fragments
(Fab`s), derived from a monoclonal parent. It additionally would eradicate any complement-
activated response by the Fc region of the antibody and orientate the antigen-binding region
effectively on the surface of the structure. Attaching cell-targeting ligands (such as antibody
fragments) to gene carriers can offer selectivity to a particular cell type/accumulation at target
tissue, and control the route of internalisation into the target cell.
Previous efforts have reported a deactivation enhanced atom transfer polymerization (De-ATRP)
approach, which can suppress the gelation and produce hyperbranched polymers from the
homopolymerization of multivinyl monomers (MVMs) 16
. Furthermore, the employment of De-
ATRP in can achieve hyperbranched transfection agent that have competitive efficiency when
compared with commercial transfection agents 17
. Based on these observations, it is hypothesized
that a co-polymer composed of a linear poly (dimethylamino) ethyl methacrylate (pDMAEMA)
block and a hyperbranched poly (ethylene glycol) methyl ether acrylate (PEGMEA) based unit
with poly (ethylene glycol) diacrylate (PEGDA) as the MVM branching agent (pD-b-/PDA) can
reduce cytotoxicity and also offer the possibility of facile conjugation of additional functional
groups by Michael-type addition.
Therefore, the objectives of the work presented in this chapter are:
i. Synthesize a block co-polymer composed of a linear poly (dimethylamino) ethyl methacrylate
(pDMAEMA) block and a hyperbranched poly (ethylene glycol) methyl ether acrylate
Delivering Exogenous miRNA
62
(PEGMEA) based unit with poly (ethylene glycol) diacrylate (PEGDA) as the MVM
branching agent (pD-b-/PDA) using De-ATRP synthesis. This resultant pD-b-/PDA will be
characterized during polymer synthesis using gel permeation chromatography and its structure
evaluated using proton nucleic magnetic resonance (1H NMR).
ii. Demonstrate effective complexation of miR mimics with pD-b-/PDA by characterising its
electrophoretic mobility, prove and demonstrate Michael-type addition of thiols to pD-b-/PDA
using Ellman‟s Assay, and antibody fragments to pD-b-/PDA and by SDS PAGE.
iii. Optimise and deliver miRs with pD-b-/PDA to effect silencing in a dual reporter system of
Renilla Luciferase and Firefly Luciferase using cardiac fibroblasts as an experimental cell
type.
2.2 Materials and Methods
2.2.1 Materials
All laboratory consumables were obtained from Sigma Aldrich (Dublin, Ireland), unless
Figure 2.5: 1H NMR spectra of pD-b-P/DA used to confirm the branching structure of pD-b-
P/DA synthesized from a linear pDMAEMA (acting as a macro initiator) by in situ DE-ATRP.
From this spectra, the structure pD-b-P/DA was evaluated by integrating the peaks present in
the spectra and applying these integrals to Equations 2.2.
Chemical Shift
Linear pDMAEMA
PEGMEA Branched PEGDA
PEGDA
Delivering Exogenous miRNA
77
Equations 2.2
DMAEMA Component (n) =
PEGMEA Component (m) =
PEGDA (free vinyl) Component (x) =
Branching PEGDA Component (y) =
Total Content
Therefore, the percentage of each component within the polymer structure is a percentage of
the Total Content, for instance:
% DMAEMA
Table 2.2: Polymer composition as calculated from 1H NMR peak area by Equations 2.1.
Polymer Composition by 1H NMR (%)
DMAEMA PEGMEA Branching PEGDA Free Vinyl
68 19.5 12.45 3.1
2
g
3
i
3
fed
)242( mxnc
yxmn
yxmn
n
Delivering Exogenous miRNA
78
Figure 2.6: pD-b-P/DA binding ability of miR mimic at increasing w:w ratios (0.5:1 → 20:1)
demonstrated by representative acrylamide gel electrophoresis; vertical arrow indicates
direction of charge. (a) Negatively charged RNA migrates towards the anode (- negative)
whereas binding with pD-b-P/DA facilitates electrostatic interaction causing a net positive
charge of RNA and the RNA travels towards the cathode (+ positive). Complete shift in
electrophoretic mobility begins at a w:w ratio of 5:1 however there is RNA present towards the
cathode at lower w:w ratios but complete binding does not occur at the lower w:w ratios.
Verification of complexation observed in (a) was performed by reversing the charge terminals
in (b) and the same observations occur.
a
b
Delivering Exogenous miRNA
79
Figure 2.7: pD-b-P/DA significantly consumes cysteine compared to PEI (control) after 30
minutes as measured indirectly using Ellman’s assay. There is a slight reduction in μmoles of
cysteine after 30 minutes, however this can be attributed to possible oxidation of the cysteine or
formation of di-sulphide bonds between the cysteine and itself. Consumption occurs through
Michael-type addition of thiols with the double carbon bond present in pD-b-P/DA. Data
presented is the mean ± standard deviation, n = 4.
0 0.5 1 2 3
2
4
6
8
10
pD-b-P/DAPEI
Incubation Time (hours)
m
ole
s C
yste
ine
Delivering Exogenous miRNA
80
Figure 2.8: SDS acrylamide gel of pD-b-P/DA conjugated with CD90 antibody Fab`s at molar
ratios of pD-b-P/DA reacted with moles thiol from antibody Fab’s (determined using Ellmans
assay), under non-reduced conditions and reduced conditions (treatment with β-
mercaptoethanol to separate the heavy (CH) and light (CL) of the antibody fragments). Non-
reduced conditions reveal an increase in molecular weight of the Fab`s due to conjugation with
pD-b-P/DA due to the slower migration of the bands which is most evident at a 2:1 molar ratio.
Additionally, under reduced conditions, the heavy chain (CH) of the antibody fragment also has
an increased molecular weight due to the conjugation of pD-b-P/DA.
Delivering Exogenous miRNA
81
)(
)(
controlnegativecontrolpositive
controlnegativesample
RatioRatio
RatioRatioRI
Relative Inhibition:
Figure 2.9: Verification of reporter system with pmiR-29B (plasmid encoding firefly luciferase
with miR-29B target). miR-29B delivery effectively knocks down Firefly luciferase in target
pmiR-29B transfected cardiac fibroblasts compared to pmiR-Control (unmodified plasmid) and
delivery of scrambled miR. Data presented is the mean ± standard deviation, n = 6. * indicates a
statistically significant knockdown compared to all other groups, p < 0.05.
miR-29B miR-Scram no miR0.0
0.5
1.0
1.5
pmiR-29BpmiR-Control
*
Rela
tive In
hib
itio
n
Delivering Exogenous miRNA
82
Figure 2.10: Optimisation of Dharmafect™
to miR-29B mimic w/w ratio by evaluating relative
inhibition using reporter luciferase plasmid (left y-axis) and cellular metabolic activity through
alamarBlue® metabolic oxidative reduction (right y-axis). The most significant knockdown of
normalized expression occurs at a w/w ratio of 2:1 while maintaining appropriate cellular
metabolic activity. A constant weight of 300 ng of miR-29B mimic was used in this experiment.
Higher w/w ratios result reduced metabolic activity and also less relative inhibition. Data
presented is the mean ± standard deviation, n = 4. * indicates a statistically significant
knockdown compared to all other groups, p < 0.05.
0.5:
11:
11.
5:1
2:1
3:1
4:1
0.0
0.5
1.0
*
*
No miR Naked miR
miR complexed with Dharmafect
No
rmalized
Exp
ressio
n
0
20
40
60
80
100
**
Cellu
lar
Meta
bo
lic In
dex (
%)
*
0.5:1 1:1 1.5: 1 2:1 3:1 4:1
Rela
tiv
e I
nh
ibit
ion
Delivering Exogenous miRNA
83
Figure 2.11: Optimisation of Dharmafect™
complexed miR-29B dose in terms of μg RNA
delivered at a w/w of 2:1 Dharmafect™
: miR mimic. Relative inhibition was evaluated using
reporter luciferase plasmid (pmiR-29B, left y-axis) and cellular metabolic activity through
alamarBlue® metabolic oxidative reduction (right y-axis). The most significant relative
inhibition occurs at a dose of 0.3 and 0.35 μg while maintaining appropriate cellular metabolic
activity. Higher miR-29B doses result in a reduction in metabolic activity toxicity and also an
increase in relative inhibition which is due ot the increased Dharmafect™
that the cells are
subjected to. Data presented is the mean ± standard deviation, n = 4. * indicates a statistically
significant knockdown compared to all other groups, p < 0.05.
100
ng
150
ng
200
ng
250
ng
300
ng
350
ng
400
ng
500
ng 0.0
0.5
1.0
no miR miR complexed with Dharmafect
* *
No
rmalized
Exp
ressio
n
40
60
80
100
* *
Cellu
lar
Meta
bo
lic In
dex (
%)
0.1 0.15 0.2 0.25 0.3 0.35 0.4 0.5 (μg RNA complexed at w/w ratio of 2:1)
Rela
tiv
e I
nh
ibit
ion
Delivering Exogenous miRNA
84
Figure 2.12: Relative inhibition of reporter luciferase (left y-axis) in response to naked miR-
29B, miR-29B complexed at varying w/w ratios with pD-b-P/DA and controls. Also presented is
the effect of miR-29B complexed with pD-b-P/DA and controls with on cellular metabolic
activity (right y-axis). Data presented is the mean ± standard deviation, n = 4. * represents a
statistically significant difference at p< 0.05.
0.5:1 1:1 2:1 4:1 8:10.0
0.2
0.4
0.6
0.8
1.0
* *
No miR
Naked miR miR complexed with pD-b-P/DA
miR complexed with Dharmafect
No
rmalized
Exp
ressio
n
50
60
70
80
90
100
*
*
Cellu
lar
Meta
bo
lic In
dex (
%)
Rela
tiv
e I
nh
ibit
ion
Delivering Exogenous miRNA
85
Figure 2.13: Antibody fragment conjugation does not affect the complexation of pD-b-P/DA
with RNA. Representative agarose gel electrophoresis of immunopolyplexes (decorated with
antibody fragments). Each lane is labelled according to the w/w ratio of pD-b-P/DA: miR mimic.
Negatively charged, uncomplexed miR mimic migrates towards the anode (- negative) terminal
whereas miR mimics that are complexed with pD-b-P/DA undergo a change in electrophoretic
mobility as they become positively charged and travel towards the cathode (+ positive). There is
a separation at w/w ratios of 2:1 and 4:1 (i.e. two distinct bands in the same lane) as some, but
not all miR mimics have become complexed with pD-b-P/DA and therefore the free negative
RNA migrates towards that anode and the positive pD-b-P/DA complexed RNA travels towards
the cathode.
0.5:1 1 :1 2:1 4 :1 5:1 blank
+
-
miR alone
Delivering Exogenous miRNA
86
Figure 2.14: Relative inhibition of reporter luciferase from cardiac fibroblasts (white bars) and
HUVECS (black bars) pre-transfected with pmiR-29B and subsequently treated with miR-29B
in different formulations. Data presented is the mean ± standard deviation, n = 4. * indicates a
statistically significant difference at 48 hours compared to other groups at that time point (p <
0.05).
0.0
0.2
0.4
0.6
0.8
1.0
pD-b-P/DA - miR pD-b-P/DA - Fab` - miR
DharmafectTM -
miR
*
48 hours 96 hours
No
rmalized
Exp
ressio
n
48 hours 96 hours
pD-b-P/DA-miR pD-b-P/DA-Fab`-miR
Dharmafect™ - miR
Rela
tiv
e I
nh
ibit
ion
Delivering Exogenous miRNA
87
Figure 2.15: Cellular metabolic activity derived from alamarBlue® reduction of cardiac
fibroblasts (white bars) and HUVECS (black bars) pre-transfected with pmiR-29B and
subsequently treated with miR-29B in different formulations. Data presented is the mean ±
standard deviation, n = 4. No significant difference was detected between any of the groups.
0
50
100
pD-b-P/DA - miR pD-b-P/DA - Fab` - miR
DharmafectTM -
miR
48 hours 96 hours
Cellu
lar
Meta
bo
lic In
dex (
%)
48 hours 96 hours
pD-b-P/DA-miR pD-b-P/DA-Fab`-miR
Dharmafect™ - miR
Delivering Exogenous miRNA
88
together with slower migration of Fab` above demonstrates that conjugation of Fab`s with pD-b-P/DA
has occurred, thereby increasing the molecular weight of the heavy chain of the Fab`. To monitor the
efficacy of this system in silencing a gene of interest by delivering exogenous miRs, a dual-luciferase
miR target expression vector (pmiRGLO™
, Promega Ltd., UK) was employed. pmiRGLO™
was
digested, linearized and ligated with a target sequence of rodent miR-29B. To confirm digestion, the
original plasmid, and the modified plasmid (pmiR-29B) were incubated with target (miR-29B) and
control mismatched sequences (miR-Scram) (Figure 2.10). Significant silencing was observed when
miR-29B was delivered to cells pre-transfected with pmiR-29B. Furthermore, the pmIR-29B was
sequenced (see Appendix G.9 for sequencing results) and verified to contain the ligated sequence. The
conditions of the Dharmafect™ preparation were optimized beginning with optimization of w/w ratio
and following this the quantity of complexes that could be delivered. This optimization was assessed
by evaluation of silencing (normalized transfection) and cellular metabolic activity. The appropriate
w/w ratio was first determined to be 2:1 (Figure 2.11). Following this, the least toxic w/w ratio was
tested to determine the most effective dose without compromising cellular viability. The most
significant silencing of the normalized luciferase expression occurred at masses of 300 ng and 350 ng
of miR mimic complexed at a w/w ratio of 2:1 with Dharmafect™
(Figure 2.12).
Based on this data, it was decided to use a mass of 330 ng of miR mimic complexed at a w/w ratio of
2:1 with Dharmafect™
in all subsequent studies. Using this reporter plasmid, the optimum w/w ratio
for delivering miR with pD-b-P/DA was determined by measuring and normalizing the knockdown of
Firefly Luciferase (miR target) compared to Renilla Luciferase in primary neonatal rat cardiac
fibroblasts. Significant normalized transfection (knockdown) occurred at w/w ratios of 8:1 and 10:1
(pD-b-P/DA/miR) compared to controls (no treatment and naked miR-29B), which was comparable to
knockdown achieved using a commercially available control (Dharmafect™
). Analysis of cellular
metabolic activity using alamarBlue® assay showed a reduction in metabolic activity (consistent with
the use of pD-b-P/DA, regardless of weight used) but this activity was significantly less than
cytotoxicity induced by the use of commercially available Dharmafect™
(Figure 2.10).
Finally, pD-b-P/DA conjugated with Fab`s was complexed with miR-29B at a w/w ratio of 8:1. To
verify the efficiency of knockdown using this platform, rat neonatal cardiac fibroblasts were again
subjected to the reporter transfection assay. Human umbilical vein endothelial cells (HUVECs) were
subjected to the same experimental controls as they have a minimal expression of the CD90 antigen
(towards which the antibody fragment binds) and are not responsive to an antibody directed towards
rat. Significant knockdown occurred at 48 hours with Fab` decorated complexes compared to pD-b-
P/DA with no Fab`s and also compared to the commercially available control (Dharmafect™
) in rat
cardiac fibroblasts. However, this effect was not seen at 96 hours. As all complexes remain in each
Delivering Exogenous miRNA
89
well during the duration of a study, it is hypothesized that in the first time point (48 hours) the Fab`
decorated complexes have adhered quicker to their target cell and have been internalized before those
with no Fab`. Therefore silencing occurs quicker. However, at the 96 hour time point it is probable
that all complexes have adhered to the cells due to the charge interaction of the complexes with the
cell membrane and therefore no statistically significant difference can be detected between Fab`
decorated complexes and non-Fab` decorated complexes. No effect of Fab` decorated complexes was
observed in HUVECs (Figure 2.15). Additionally, no significant difference was observed between any
of the groups at 48 hours or between any of the groups at 96 hours with regard to cellular metabolic
activity with addition of the complexes (Figure 2.16).
2.4 Conclusion
The development of non-toxic, efficient, and clinically relevant delivery systems remains an
important challenge for the clinical applications of interfering RNA-based therapeutics. In this study
synthesis of a hyperbranched multi-vinyl polymer was achieved by controlling ATRP in deactivation
enhanced mode by employing L-AA as a reducing agent and using a macro-initiator (in this case
pDMAEMA) achieving a co-polymer system using DE-ATRP. This reaction was monitored using
GPC and the structure of the synthesized pD-b-/PDA was evaluated using 1H NMR. In this study, the
efficacy of a miR mimic delivery platform that is based on a cationic interaction of pDMAEMA
tertiary amines and phosphates present in the backbone of the miR was demonstrated. This interaction
was monitored and verified using agarose gel electrophoresis. The presence of double carbon bond
sites as potential acceptor units in a relatively mild but highly efficient Michael type addition (as
described in Figure 2.2) enabled the conjugation of antibody fragments to this system, which was
demonstrated using SDS-PAGE and enabled improved delivery and efficacy of miRs (as verified by
knockdown in normalized transfection in cardiac fibroblasts at 48 hours). This method opens up a
plethora of options where this platform can be employed and tuned toward functionalization
strategies. Realistically, any SH-terminated moiety can act as a Michael donor for conjugation to the
pD-b-/PDA synthesized and characterized in this chapter. This encompasses any monoclonal antibody
reduced to form Fab`s, peptides engineered to have cysteine terminations, and also scFvs selected and
amplified using phage display technology 20
to produce effective targeting molecules. Presented here
in this chapter, is demonstrative data proving the efficacy of this system which will be tested towards
a functional application in the proceeding chapters.
Delivering Exogenous miRNA
90
2.5 References
1. Shan X, Lin X, Fu H, Deng Y, Zhou L, Zhu N, Liu Y, Zhang Y, Li Y, Lin S-G, Yu Y. Upregulated expression of miR-1/miR-206 in a rat model of myocardial infarction. Biochem.
Biophys.l Res. Comm. 2009;381:597-601
2. Trang P, Wiggins JF, Daige CL, Cho C, Omotola M, Brown D, Weidhaas JB, Bader AG,
Slack FJ. Systemic delivery of tumor suppressor microRNA mimics using a neutral lipid emulsion inhibits lung tumors in mice. Mol. Ther. 2011;19:1116-1122
3. van Rooij E, Sutherland LB, Thatcher JE, DiMaio JM, Naseem RH, Marshall WS, Hill JA,
Olson EN. Dysregulation of microRNAs after myocardial infarction reveals a role of miR-29 in cardiac fibrosis. Proc. Nat.Acad. Sci. 2008;105:13027-13032
2004;304:594-596 5. Monaghan M, Pandit A. RNA interference therapy via functionalized scaffolds. Adv. Drug
Del. Rev. 2011;63:197-208
6. Manjunath N, Wu H, Subramanya S, Shankar P. Lentiviral delivery of short hairpin RNAs.
Adv. Drug Del. Rev. 2009;61:732-745 7. Tomlinson E, Rolland AP. Controllable gene therapy pharmaceutics of non-viral gene
delivery systems. J. Controlled Release. 1996;39:357-372
8. Rahbek UL, Howard KA, Oupicky D, Manickam DS, Dong M, Nielsen AF, Hansen TB, Besenbacher F, Kjems J. Intracellular siRNA and precursor miRNA trafficking using
bioresponsive copolypeptides. J. Gene Med. 2008;10:81-93
9. Xu D, Takeshita F, Hino Y, Fukunaga S, Kudo Y, Tamaki A, Matsunaga J, Takahashi R-u,
Takata T, Shimamoto A, Ochiya T, Tahara H. Mir-22 represses cancer progression by inducing cellular senescence. J. Cell Biol. 2011;193:409-424
10. Pramanik D, Campbell NR, Karikari C, Chivukula R, Kent OA, Mendell JT, Maitra A.
Restitution of tumor suppressor microRNAs using a systemic nanovector inhibits pancreatic cancer growth in mice. Mol. Cancer Ther.. 2011;10:1470-1480
11. Huang H, Bao Y, Peng W, Goldberg M, Love K, Bumcrot DA, Cole G, Langer R, Anderson
DG, Sawicki JA. Claudin-3 gene silencing with siRNA suppresses ovarian tumor growth and metastasis. Proc. Nat. Acad. Sci. 2009;106:3426-3430
12. Davis ME, Zuckerman JE, Choi CHJ, Seligson D, Tolcher A, Alabi CA, Yen Y, Heidel JD,
Ribas A. Evidence of RNAi in humans from systemically administered siRNA via targeted
nanoparticles. Nature. 2010;464:1067-1070 13. Kim SH, Jeong JH, Lee SH, Kim SW, Park TG. Local and systemic delivery of VEGF siRNA
using polyelectrolyte complex micelles for effective treatment of cancer. J. Controlled
Release. 2008;129:107-116 14. Nelson AL, Dhimolea E, Reichert JM. Development trends for human monoclonal antibody
therapeutics. Nat. Rev. Drug Discov. 2010;9:767-774
15. Heggli M, Tirelli N, Zisch A, Hubbell JA. Michael-type addition as a tool for surface functionalization. Bioconjugate Chem.. 2003;14:967-973
16. Zheng Y, Cao H, Newland B, Dong Y, Pandit A, Wang W. 3D single cyclized polymer chain
structure from controlled polymerization of multi-vinyl monomers: Beyond flory–stockmayer
theory. J. Amer. Chem. Soc. 2011;133:13130-13137 17. Newland B, Zheng Y, Jin Y, Abu-Rub M, Cao H, Wang W, Pandit A. Single cyclized
molecule versus single branched molecule: A simple and efficient 3D “knot” polymer
structure for nonviral gene delivery. J. Amer. Chem. Soc. 2012;134:4782-4789 18. Newland B, Tai H, Zheng Y, Velasco D, Di Luca A, Howdle SM, Alexander C, Wang W,
Pandit A. A highly effective gene delivery vector - hyperbranched poly(2-
(dimethylamino)ethyl methacrylate) from in situ deactivation enhanced ATRP. Chem.
Commun. 2010;46:4698-4700
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19. Lu B, Mahmud H, Maass AH, Yu B, van Gilst WH, de Boer RA, Silljé HHW. The PLK1
inhibitor BI 2536 temporarily arrests primary cardiac fibroblasts in mitosis and generates aneuploidy PLoS ONE. 2010;5:e12963
20. O‟Dwyer R, Razzaque R, Hu X, Hollingshead S, Wall J. Engineering of cysteine residues
leads to improved production of a human dipeptidase enzyme in E. Coli. App. Biochem.
Biotech. 2009;159:178-190
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Chapter Three
An Injectable Scaffold Delivery System
The majority of this chapter is due to be submitted for publication in:
Monaghan M, Browne S, Schenke-Layland K, Pandit A. A biodegradable crosslinked scaffold as a delivery platform of
exogenous microRNAs- in vitro and in vivo evaluation. Submitted to Mol. Ther.
An Injectable Scaffold Delivery System
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3.1 Introduction
Biomaterial based scaffolds have played a central role in regenerative medicine and tissue
engineering and several key requirements for scaffolds have been identified. It is desirable that
scaffolds fabricated from a range of natural and synthetic materials be biodegradable to obviate
the need for a removal procedure. In tandem, predictable biodegradation of the scaffold can
facilitate controlled release of biomolecules embedded within the scaffold. Degradation of the
scaffold can create a path for tissue ingrowth and this can be further facilitated by a highly porous
scaffold which can also allow for the initial transport of oxygen and nutrients as well as for the
removal of metabolic waste and degradation products.
The current paradigm of tissue engineering incorporates the use of biomolecules, which can
include growth factors, pharmaceutical agents, or mediators of gene therapy. Scaffolds can act as
reservoirs in the delivery of RNAi1. RNAi delivery from a scaffold enables localized treatment, as
the scaffold, acting as a reservoir of RNAi facilitates enhanced delivery of this therapeutic
molecule than would be the case with intravenous delivery strategies which include systemic
delivery in unprotected formulations 2, 3
. Targeting a cell population or anatomical location by
injection or systemic delivery is complex and poses many challenges; direct delivery of a therapy
from a scaffold, however, can surmount these barriers. Cells in a target tissue, surrounding a
scaffold acting as a reservoir, become exposed to the therapeutic load within the scaffold limiting
unwanted exposure in other areas. In addition, scaffold-based delivery has the potential to
maintain effective levels of payload and nucleotide bioactivity for extended periods which
broadens the opportunity for cellular internalization and increases the likelihood of transfection.
Delivery from most scaffolds occurs by means of a combination of therapeutic payload (in this
case RNA) interaction with the scaffold and subsequent release through degradation of the
scaffold, with the payload and material properties having a significant influence on these
interactions.
The focus of this chapter is with miR-29B of the miR-29 family. This class of miRNAs has been
specifically associated with the regulation of fibrosis in a number of tissues including renal 4,
bone 5, pulmonary
6, hepatic
7 and cardiac tissue
8. miR-29B has also been elucidated to have a
significant role in remodeling extracellular matrix tissue, possessing a significant relationship
with collagen production 8.
A key requirement associated with the encapsulation of RNAi and non-viral vectors is that the
scaffold fabrication method must be compatible with the biomolecules and vector integrity.
An Injectable Scaffold Delivery System
94
Methods to achieve this fabrication can involve high temperatures, organic solvents and the
generation of free radicals or shear stresses that may damage the payload. Even if the nucleic acid
(pDNA or RNA) is stably encapsulated, it can still be damaged by the degradation products 9. The
release kinetics of encapsulated RNAi from scaffolds is also reliant upon a number of factors such
as the concentration of the scaffold, its degree of crosslinking, and the scaffold material which can
make its degradation responsive to pH, temperature, cellular enzymatic products and/or
hydrolysis 10
. This degradation rate can influence the time-course release of the embedded RNAi
as the scaffold loses volume and becomes assimilated by surrounding tissue 11
. Although the
advent of RNAi-based therapy is relatively recent, there have, nevertheless, been numerous efforts
to deliver this therapy via scaffolds and hierarchical structures. The use of scaffolds as a reservoir
of RNAi has been illustrated in many studies because of their potential as an injectable system for
therapeutics which assume the shape of irregular spaces and defects 12-15
.
In order to improve stability and mechanical properties of scaffolds, cross-linkers such as
glutaraldehyde and carbodiimide have been used to modify the chemico-physcial properties of
these scaffolds. However, these molecules have been shown to be highly toxic, limiting their use
in implantable scaffolds 16
. Consequently, different approaches using non-toxic chemical cross-
linkers have been developed and in particular the use of poly (ethylene glycol) ether tetra-
succinimidyl glutarate (4S-StarPEG) has been advocated 17, 18
.
Herein, a number of concepts within one platform for the effective silencing of protein using non-
viral double stranded miRs are presented in this chapter. A method to formulate an atelocollagen
type I scaffold crosslinked using a 4S-StarPEG which is non-toxic and gels in situ is described.
The use of scaffolds for the viral and non-viral delivery of therapeutic genes is well established in
the literature 19-21
. However, using a scaffold as a reservoir of exogenous miRs has not, been
previously reported. Therefore, it is hypothesized that an atelocollagen type I scaffold crosslinked
with 4S-StarPEG can act as a reservoir of miR-29B in naked form, miR-29B complexed with a
poly (2-(dimethylamino) ethyl methacrylate) (pDMAEMA) based polymer (pD-b-P/DA-
developed in Chapter Two) and miR-29B complexed with PEI. This scaffold/miR platform will
effectively silence ECM proteins; namely collagen type I and collagen type III.
Therefore, the objectives of the work presented in this chapter are to:
i. Develop an atelocollagen type I scaffold and characterise the effect of crosslinking that
can be achieved using 4S-StarPEG by determining the amine content of the scaffolds
using a trinitrobenzenesulfonic acid (TNBSA) assay, the effect on the degradation profile
An Injectable Scaffold Delivery System
95
of the scaffolds using collagenase degradation and the effect on mechanical properties
using rheology.
ii. Investigate the effect of crosslinker density on the release profile of interfering RNA from
scaffolds and the effect of complexing the RNA with a complexing agent on the release of
the RNA from the scaffolds, spectrophotometrically, using Cy™
3 labeled siRNA.
iii. Investigate the ability of this scaffold acting as a reservoir in vitro of miR-29B,
characterising its release profile and the subsequent effect of silencing collagen type I and
type III expression in vitro.
3.2 Materials and Methods
3.2.1 Materials
All solvents were of analytical or HPLC grade and were obtained from Sigma Aldrich Chemical
Company (Dublin, Ireland) unless otherwise stated. All oligonucleotides and primers were
purchased from Eurofins MWG GmbH (Ebersberg,Germany). 4S-StarPEG (Mw = 10,000) was
purchased from JenKem Technology Co. Ltd.(Texas, USA).
3.2.2 Collagen Scaffold Preparation
Atelocollagen was isolated as described elsewhere 22
(Appendix D). Nine parts of collagen
solution (3.5 mg/ml w/v) was gently and thoroughly mixed with one part of 10 X phosphate
buffered saline (PBS). The solution was neutralised by the drop-wise addition of 2 M sodium
hydroxide (NaOH) until a final pH of 7–7.5 was reached and kept in an ice bath to delay hydrogel
formation. 4S-StarPEG was then added to final concentrations of 0.125 mM, 0.25 mM, 0.5 mM, 1
mM and 2 mM but always in a volume of 50 μl. 0.625% glutaraldehyde (GTA) was used as a
positive control. The solutions were incubated for one hour at 37 °C in a humidified atmosphere
to induce gelation. See Appendix D.3 for detailed protocol.
3.2.3 TNBSA Assay
The primary amine groups of type I atelocollagen scaffolds were determined using 2, 4, 6-
Trinitrobenzenesulfonic acid (TNBSA) detection assay as previously described23-24
. Briefly, after
crosslinking and hydrogel formation, the scaffolds were incubated in 0.1 M sodium bicarbonate
pH 8.5. 0.01 % of TNBSA was added to the samples and incubated for two hours at 37 °C. The
reaction was stopped using 10 % sodium dodecyl sulphate (SDS) and 1 M hydrochloric acid
(HCl). The scaffolds were then incubated at 120 °C for 15 minutes. Absorbance of each sample
An Injectable Scaffold Delivery System
96
was read at 335 nm and the free amine groups quantified by interpolating values from a linear
standard curve of known concentrations of glycine. See Appendix D.4 for detailed protocol.
3.2.4 Degradation by Collagenase
Resistance of the scaffolds to enzymatic digestion was evaluated using collagenase assay 25
.
Briefly, scaffolds were incubated for one hour in 0.1 M Tris–HCl (pH 7.4), containing 50 mM
calcium chloride (CaCl2) at 37 °C. Subsequently, bacterial collagenase type IV (770 units/mg,
extracted from Clostridium histolyticum), reconstituted in 0.1 M Tris–HCl at a concentration of 10
units/mg collagen type I, was added. After incubation for 48 hours at 37 °C, the enzymatic
reaction was stopped by the addition of 0.25 M EDTA. After vacuum dehydration, the remaining
mass of the scaffolds was weighed and normalised to the remaining mass of GTA cross-linked
scaffolds. See Appendix D.5 for detailed protocol.
3.2.5 Rheological Evaluation
In order to identify the gel time of the scaffold as a function of cross-linking, rheological
measurements were performed at 37 °C using a Haake Modular Advanced Rheometer System™
(MARS) rheometer (Thermo Haakes, Germany) previously described 26
. Briefly, type I
atelocollagen, 10 X PBS and 1 M NaOH alone, with 0.625% GTA, or with different concentrations
of 4S-StarPEG (0.5 mM, 1 mM and 2 mM), were added to the plate at 37 °C. The rheometer was
equipped with a circulating water bath to accurately control the temperature. To minimise the
influence of water loss on mechanical behaviour, samples were coated with paraffin oil. Dynamic
frequency sweep experiments were carried out to determine the storage (G′) and loss (G″) moduli
as a function of time at 37 °C. The measurements of the storage (G′) and loss (G″) moduli during
the gelation were recorded as a function of time for five different frequencies (a, b, c, d and e
rad/s) using multi-wave facilities. The gel point was defined as the time that G′ equaled G″.
3.2.6 Complexation
miR-29B mimic and negative control scrambled miR mimic (miR-scram) were obtained from
Qiagen with the sequences for rno-miR-29B: 5`-uagcaccauuugaaaucaguguu-3`; and a control
scrambled mimic: 5`-gtgctctcattaacgtaaattga-3`. miR mimics were mixed individually with pD-b-
P/DAand poly (ethylenimine) (PEI; 25 kDa) at w/w ratios of 8:1 and 2:1 respectively. The
components were mixed and complexes allowed to form at room temperature for 60 minutes in
serum free media. Complexation was analysed by acrylamide gel electrophoresis (see Appendix K
for detailed protocol). For monolayer culture experiments, 333 ng of miRs were complexed and
added to each well of a 96 well plate in a volume of 50 μl. For scaffold delivery of miRs from a
An Injectable Scaffold Delivery System
97
Figure 3.1: Type I atelocollagen and 4S-StarPEG reaction. Succinimidyl glutarate is an
NHS-ester which binds with amine groups and therefore the succinimidyl groups react with
the amine groups present on the molecules of type I atelcollagen at 37 °C.
Bovine Type I
Atelocollagen
Four-arm, Succinimidyl-Glutarate Terminated Poly
(ethylene glycol)
Crosslinking at 37 °C with Free Amines
Present in Atelocollagen
An Injectable Scaffold Delivery System
98
collagen type I scaffold crosslinked with 4S-StarPEG at a molar ratio of 1:1, 2 μg of miRs were
complexed and mixed evenly to the crosslinked scaffold solution on ice before gelation occurred.
3.2.7 Fab` Conjugation
Antibody fragments (Fab`s) were derived from monoclonal antibodies as described in Chapter
Two. Known molar concentrations (deduced from Ellman’s assay) of these Fab`s were reacted
with pD-b-P/DA in a reaction buffer of 0.2 mM NaH2PO4 with 1 mM EDTA at pH 8.0 (purged
prior to reaction with argon for 30 minutes). Briefly, reactions were performed in which molar
ratios of Fab` thiol concentration (from Ellman’s assay) and moles of free vinyls (calculated from
1H NMR data presented in Chapter Two) were reacted at a ratio of 1:1.
3.2.8 Elution Studies
The characterization of the 4S-StarPEG collagen type I scaffold’s release profile of interfering
RNA was performed using siRNA as a model oligonucleotide labeled with Cy™
3. Previous
experiments using intercalating staining of oligonucleotides with PicoGreen® proved unreliable as
the use of the complexing agents hindered the binding of this agent to the nucleic acid, an
observation which is noted in pDNA release studies 27
. siRNA was labeled using Silencer siRNA
Labeling Kit Cy™
3 (Ambion®/Life Technologies, Dublin, Ireland) according to the
manufacturer’s instructions (Appendix V for detailed protocol). Release of the miRNA complexes
was evaluated using the fluorescence from the control siRNA, which was labeled with Cy™
3.
Briefly, the scaffolds were prepared as described above, in a 48-well plate with the additional step
of adding 2 μg of Cy™
3 labeled siRNA. Three groups were investigated in this study: naked
siRNA, siRNA complexed with pD-b-P/DA and siRNA complexed with PEI. In addition the
effect of crosslinking density on the release profiles of siRNA from the scaffolds was investigated
using three conditions: a crosslinking density of 1 mM, 0.5 mM and 0.05 mM. The loaded
scaffolds were incubated for two hours at room temperature to allow the complexes to associate
with the scaffold and for complete gelation to occur. Thereafter, the scaffolds were individually
removed and transferred to the bottom of a 24-well well plate. To this, an equal volume of tris
(hydroxymethyl) aminomethane-n/ethylenediaminetetraacetic acid (Tris–EDTA) buffer (10 mM
Tris–HCl and 1 mM EDTA, pH = 7.5) was added. At each time point, this process was repeated.
At the end of the experiment, the siRNA content of the solutions was quantified by measuring the
fluorescence with a Varioskan Flash® spectral scanning multimode reader (Thermo Scientific,
Vantaa, Finland) and the cumulative release of siRNA complexes from the scaffold was
calculated following comparison with a standard curve.
An Injectable Scaffold Delivery System
99
3.2.9 Evaluating Matrix Binding of RNA complexes
To further understand the mechanism of how RNA complexes are held within the scaffold the
electrophoretic kinetics of RNA complexes within the scaffold were evaluated using agarose gel
electrophoresis. 1 % (w/v) agarose was heated in tris-acetic acid-Ethylenediaminetetraacetic acid
(EDTA) buffer (40 mM Tris, 20 mM acetic acid, and 1 mM EDTA respectively) and a 10,000 fold
dilution of Syber®Safe dye was added prior to gel casting. Non-crosslinked atelocollagen
scaffolds or scaffolds crosslinked with 4S-StarPEG, to a volume of 10 μl, were deposited into the
running wells of this gel with 330 ng of naked RNA, RNA complexed with pD-b-P/DA, or
complexed with PEI. Naked RNA and scaffolds containing no RNA were applied as controls.
Additionally, naked RNA mixed with an indicative loading buffer was run to monitor the
migration of the RNA on the gel. However, this was not applied to the other samples to avoid any
interference with the kinetics of the scaffolds. A voltage of 50 V was applied to the agarose gel
and the current was set to ‘auto’. After 20 minutes the loading buffer indicated sufficient
migration to observe the electrophoretic mobility of the complexes under UV light.
3.2.10 Cell Extraction
Rat cardiac fibroblasts were isolated from neonatal pups as previously described 28
(Appendix
I.8). Briefly, neonatal rat ventricle myocytes were isolated from the cardiac ventricles of three to
five days old Sprague-Dawley pups. Hearts were removed from the thoracic cavity and placed in
a tube containing cold (4-(2-hydroxyethyl)-1-piperazineethanesulfonic acid) HEPES solution (20
mM HEPES, pH 7.4). Ventricles were separated from surrounding tissue using scissors and
minced into several pieces. Subsequently cardiomyocytes and fibroblasts were detached from the
extracellular matrix by repeated incubation in collagenase, supplemented with 2 mg/ml trypsin
and 20 µg/ml DNase. Cells were collected by centrifugation and tissue clumps were removed by
filtration. The cells were then pre-plated in cell culture dishes in 50 ml Dulbecco's Modified Eagle
Medium (DMEM) /F12 (50:50) medium with 5% fetal bovine serum (FBS) for 45 minutes.
During this period, most non-cardiomyocyte cells (mainly fibroblasts) attached to the dish,
whereas cardiomyocytes remained in solution. Fibroblasts were subsequently cultured in
DMEM/F12 medium containing 10% FBS.
3.2.11 Monolayer Silencing Study
Primary rat cardiac fibroblasts were seeded on a six-well plate at a density of 1 x 106
cells per
well. After one day incubation at 37 °C, 5% CO2, to ensure adherence and acclimatization, miR-
29B or miR-scram; uncomplexed, complexed with pD-b-P/DA or complexed with PEI were added
to each well in a total volume of 250 μl with a concentration of 0.5 μg of miR. After ten minutes,
An Injectable Scaffold Delivery System
100
the total volume in the wells was brought to 1 ml with the addition of DMEM/F12 containing
FBS at a concentration of 5%. The experiment was maintained for 48 hours after which samples
were processed for gene or protein analysis via RT-PCR and Western blot respectively.
3.2.12 Scaffold Delivery Silencing Studies
Silencing studies were performed on six-well well plates seeded with 1 x 106 cells per well. After
one day incubation to ensure adherence and acclimatization, scaffolds were placed onto the cells.
In total 250 μl of scaffold solution was applied to each well. The scaffolds were applied directly
to ensure direct contact with cells and also to bring about a direct interaction between the cells and
the scaffold. The use of a 250 μl volume applied in a six-well enabled a very thin scaffold to be
produced which maintained diffusion of nutrients to maintain the viability of the cells.
3.2.13 RNA Extraction
RNA extraction was performed at 7, 14, and 21 days. One mL of TRI Reagent® (Applera Ireland,
Dublin, Ireland) was added to each construct and incubated for five minutes at room temperature.
Scaffolds were mechanically disrupted using a sterile pipette tip. Phase separation was performed
by adding chloroform (Sigma-Aldrich), and total RNA was purified using an RNeasy™
kit
(Qiagen), according to the supplier’s recommended procedure (Appendix S).
3. De Laporte L, Shea LD. Matrices and scaffolds for DNA delivery in tissue engineering. Adv. Drug Delivery Rev. 2007;59:292-307
4. Liu Y, Taylor NE, Lu L, Usa K, Cowley AW, Jr, Ferreri NR, Yeo NC, Liang M. Renal
medullary microRNAs in dahl salt-sensitive rats: Mir-29b regulates several collagens and related genes. Hypertension. 2010;55:974-982
5. Li Z, Hassan MQ, Jafferji M, Aqeilan RI, Garzon R, Croce CM, van Wijnen AJ, Stein JL,
Stein GS, Lian JB. Biological functions of miR-29b contribute to positive regulation of osteoblast differentiation. J. Biol. Chem.. 2009;284:15676-15684
6. Cushing L, Kuang PP, Qian J, Shao F, Wu J, Little F, Thannickal VJ, Cardoso WV, Lu J.
Mir-29 is a major regulator of genes associated with pulmonary fibrosis. Am. J. Respir.
J, Koppe C, Knolle P, Castoldi M, Tacke F, Trautwein C, Luedde T. Micro-RNAprofiling
reveals a role for miR-29 in human and murine liver fibrosis. Hepatology. 2011;53:209-218
8. van Rooij E, Sutherland LB, Thatcher JE, DiMaio JM, Naseem RH, Marshall WS, Hill
JA, Olson EN. Dysregulation of microRNAs after myocardial infarction reveals a role of
mir-29 in cardiac fibrosis. Proc. Nat. Acad. Sci. USA. 2008;105:13027-13032 9. Walter E, Moelling K, Pavlovic J, Merkle HP. Microencapsulation of DNA using
poly(DL-lactide-co-glycolide): Stability issues and release characteristics. J. Controlled
14. Kim Y-M, Park M-R, Song S-C. Injectable polyplex hydrogel for localized and long-term
delivery of siRNA. ACS Nano. 2012;6:5757-5766 15. Manaka T, Suzuki A, Takayama K, Imai Y, Nakamura H, Takaoka K. Local delivery of
siRNA using a biodegradable polymer application to enhance BMP-induced bone
formation. Biomaterials. 2011;32:9642-9648 16. Saito H, Murabayashi S, Mitamura Y, Taguchi T. Characterization of alkali-treated
collagen gels prepared by different crosslinkers. J. Mater. Sci. Mater. Med.
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17. Taguchi T, Xu L, Kobayashi H, Taniguchi A, Kataoka K, Tanaka J. Encapsulation of chondrocytes in injectable alkali-treated collagen gels prepared using poly(ethylene
glycol)-based 4-armed star polymer. Biomaterials. 2005;26:1247-1252
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38. Ogawa T, Iizuka M, Sekiya Y, Yoshizato K, Ikeda K, Kawada N. Suppression of type I
collagen production by microRNA-29b in cultured human stellate cells. Biochem. Biophys. Res. Commun. 2010;391:316-321
39. Li N, Cui J, Duan X, Chen H, Fan F. Suppression of type I collagen expression by miR-
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2012;160:451-458
Chapter Four
Evaluation of miR Delivery In Vivo
The majority of this chapter is submitted for publication in
Monaghan M, Browne S, Schenke-Layland K, Pandit A. A biodegradable crosslinked scaffold as a delivery platform of exogenous microRNAs- in vitro and in vivo evaluation. Submitted toMol. Ther.
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4.1 Introduction
A complex cascade of events follows injury aiming to repair the wound in sequential and overlapping
phases 1. This first phase begins with haemostasis in which platelets aggregate at the injury site to
form a fibrin clot. Histamine, released by ruptured cell membranes, enables blood vessels to become
dilated and porous which facilitates the infiltration of inflammatory cells such as polymorphonuclear
neutrophils (PMNs) and helper T cells into the wound site from the bloodstream 2. In the
following/overlapping inflammatory phase, bacteria and debris are phagocytised and removed.
Following this, monocytes are recruited and replace PMNs in the wound and mature into
macrophages which further phagocytise bacteria and necrotic tissue. This debris is then degraded by
protease release 3. These macrophages also secrete a number of factors such as growth factors and
other cytokines which attract cells involved in a proliferation stage of healing to the area. The
proliferative phase is characterized by angiogenesis, collagen deposition, granulation tissue formation,
epithelialisation, and wound contraction. By the end of the first week, fibroblasts become the
predominant cell in the wound and are responsible for laying down the collagen matrix at the wound
site. Formation of this granulation tissue begins in the wound during the inflammatory phase and
continues until the wound bed is covered 1. The granulation tissue consists of new blood vessels,
fibroblasts, inflammatory cells, endothelial cells, myofibroblasts, and components of a new
provisional extracellular matrix. In a final maturation and remodelling phase, collagen is remodelled
and realigned along tension lines, and cells that are not needed are removed by apoptosis as there are
reduced stress forces due to the accumulation of ECM components produced by myofibroblasts 4.
TGF-β 1 plays a significant role in matrix remodelling following injury whereby it stimulates ECM
production 5 and distinct role of miR-29B is in post-transcriptional silencing of ECM fibrillar
components stimulated by TGF-β1 6-8
. Matrix turnover, i.e. the enzymatic remodelling of ECM is an
important consideration in healing wounds and indeed remodelling components are significantly
dysregulated. Notably, MMP-8 is a collagen cleaving enzyme which functions to degrade type I, II
and III collagens 9 and in the context of wound healing; MMP-8 has been shown to be the
predominant collagenase in healing wounds and non-healing ulcers 10
. TIMP-1 complexes with
MMPs and irreversibly inactivates them by binding to their catalytic zinc co-factor and, furthermore,
TIMP-1 is a direct inhibitor of MMP-8 11
.
Adverse wound healing, such as excessive scar tissue formation, wound contraction, or non-healing
wounds represent a major clinical issue in healthcare today. A biomaterials approach can be used to
modify wound healing, acting as either matrices to support and promote tissue organization, act as
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Figure 4.1: Schematic depiction of the platform described in this chapter applied as an
injectable therapeutic. (a) Initial insult to dermis by tissue injury, (b) topical application of
treatments discussed in this chapter and (c) wound healing response to degradation of scaffold
and therapeutic release of agents embedded within the scaffold.
III/I: collagen type III to collagen type I ratio, MMP-8; matrix metalloproteinase-8, TIMP-1: tissue inhibitor of matrix metalloproteinase-1, TGF-β1: transforming grown factor-β1, Ratio: ratio of MMP-
8: TIMP-1. * indicates a statistically significant correlation, p < 0.05.
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Table 4.4: Pearson’s correlation co-efficients between parameters measured for scaffold + 0.5 μg miR-29B group.
III/I: collagen type III to collagen type I ratio, MMP-8; matrix metalloproteinase-8, TIMP-1: tissue
inhibitor of matrix metalloproteinase-1, TGF-β1: transforming grown factor-β1, Ratio: ratio of MMP-8: TIMP-1. * indicates a statistically significant correlation, p < 0.05.
Table 4.5: Pearson’s correlation co-efficients between parameters measured for scaffold + 5 μg miR-29B group.
III/I: collagen type III to collagen type I ratio, MMP-8; matrix metalloproteinase-8, TIMP-1: tissue inhibitor of matrix metalloproteinase-1, TGF-β1: transforming grown factor-β1, Ratio: ratio of MMP-
8: TIMP-1. * indicates a statistically significant correlation, p < 0.05.
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Table 4.6: Pearson’s correlation co-efficients between parameters measured for scaffold + 5 μg miR-
III/I: collagen type III to collagen type I ratio, MMP-8; matrix metalloproteinase-8, TIMP-1: tissue
inhibitor of matrix metalloproteinase-1, TGF-β1: transforming grown factor-β1, Ratio: ratio of MMP-8: TIMP-1. * indicates a statistically significant correlation, p < 0.05.
Evaluation of miR Delivery In Vivo
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regarding the direct crosstalk between miR-29B and TGF-β1 71, 72
. TGF-β1has not been established to
be a target of miR-29B. On the contrary, TGF-β1 has been suggested to downregulate endogenous
miR-29B expression 73
. Winbanks et al. found that TGF-β1 can attenuate the differentiation of
myogenic cells by increasing the expression of histone deacetylase 4 (HDAC4), a key inhibitor of
myogenic commitment. Down-regulated expression of miR-29B which acts as a translational
repressor of HDAC4 was the main determinant 73
. A similar effect has been noted in renal fibrosis
where Smad3 mediated TGF-β1 has downregulated miR-29B by binding to the promoter of miR-29 74
.
MMPs and their inhibitors; TIMPs, specifically MMP-8 and TIMP-2, play important roles in the
degradation and regeneration of wounded tissue 46
. MMPs are inactivated by TIMP-1, TIMP-2,
TIMP-3, and TIMP-4 which act by forming a 1:1 complex with the catalytic zinc in the MMPs site 47
.
It has been suggested elevation of TIMP-1may be a surrogate marker for increased ECM turnover 48
.
The scaffold with 5 μg miR-29B had the lowest level of TIMP-1 compared to the other samples, and
this decrease was statistically significant in comparison with the no treatment control and treatment
with 5 μg of miR-29B complexed with pD-b-P/DA in a scaffold. TIMP-1 is a tissue inhibitor of MMP-
1 49
and MMP-8 50
which in turn breaks down collagens type I, II and III in tissue 51
. MMP-8 was
chosen for ELISA analysis as it is established as a predominant collagenase in healing wounds 50
.
MMP-8 expression was increased in the group treated with a scaffold, containing both uncomplexed
miR-29B and miR-29B complexed with pD-b-P/DA in the membrane protein array. Conclusively, the
ELISA results show that a scaffold alone had the lowest MMP-8 expression, which was statistically
significant when compared to a scaffold with a 5 μg of uncomplexed miR-29B.
Considering the effects of the treatment groups on the ratio of MMP-8 to TIMP-1 (Figure 4.13) brings
further understanding to the results of this study. The use of a scaffold with 5 μg miR-29B resulted in
a significantly higher MMP-8: TIMP-1 ratio when compared to all other groups analysed in this
study. This suggests a number of things. Firstly, ECM remodelling is still ongoing as a ratio of 1:1
would suggest that the MMP-8: TIMP-1 ratio is balanced but with the application of a scaffold with 5
μg miR-29B; this ratio is ~1.4. Although this ratio is not excessively high, it is in much contrast to all
the other groups, the greatest of which has a MMP-8: TIMP-1 ratio of 0.5. Pearson's correlations were
obtained in order to assess whether the wound healing parameters correlated when compared to the
controls, which gave an indication of the state of healing for each treatment group (Table 4.2, 4.2, 4.4,
4.5 and 4.6) and some significant correlations were detected between wound healing events in each
group. For instance, the no-treatment group had a significant inverse relationship between granulation
volume fraction and collagen type III/I ratio which suggests that an increased granulation volume
fraction correlates with a decreased collagen type III/I ratio, which suggests more collagen type I
present in the wound bed. Additionally, a statistically significant correlation was detected between
wound contraction and the parameters TGF-β1 fold change and the MMP-8: TIMP-1 ratio. This is in
agreement with studies that associate increased TGF-β1 expression with faster wound healing 13
.
Furthermore, granulation volume fraction in the no treatment group had a statistically significant
inverse relationship with TIMP-1 fold change which is reflected in a strong correlation between
granulation volume fraction and MMP-8: TIMP-1 ratios. This indicates that remodelling and
proliferation is still quite active in this group.
Multiple regression analyses were carried out to determine whether any of the output parameters can
be predicted by measurement of another parameter. In this analysis, all the parameters that were
measured (normalised wound contraction, granulation tissue volume fraction, ratio of collagen type
III to collagen type I, TIMP-1 fold change, MMP-8 fold change, TGF-β1 fold change and the ratio of
MMP-8: TIMP-1) were cross-compared with each other. However, no statistically significant
regression trend was detected (p < 0.05). Following this, linear regression analysis was performed to
elucidate if there was a significant trend between the input parameters and the output parameters
investigated, and revealed a statistically significant correlation between uncomplexed miR-29B dose
(only when delivered through a scaffold) and the MMP-8: TIMP-1 ratio (Figure 4.13, Pearson’s
coefficient r = 0.9996, p < 0.05). This suggests that the employment of a scaffold with miR-29B
results in a modulation of wound healing in which the granulation tissue is still being remodelled, one
which is dose dependent.
The wound healing PCR array analysis revealed that a number of genes were upregulated and
downregulated which were in agreement with results from the protein membrane array and ELISAs.
Four select samples which showed significant results from the membrane protein array and ELISAs
were investigated, namely; the treatment with the scaffold alone, the treatment with 5 μg
uncomplexed miR-29B in a scaffold, the no-treatment control for comparison and healthy skin to base
the relative expression of genes. B2M, HPRT1, RPL13A, GAPDH were chosen as internal
housekeeping controls within each sample group. For ease of representation, the genes which were
upregulated and also downregulated are presented in the form of Venn diagram in Figure 4.15; a cut
off of a fold change of five was chosen. The Venn diagrams present the number of genes that are
upregulated or downregulated independently by a treatment, those that are commonly upregulated or
downregulated between two groups, and those that are commonly upregulated or downregulated by
all three groups. Gene expression analysis of the scaffold alone versus the scaffold with 5 μg
uncomplexed miR-29B was conducted to investigate further the mechanism underlying improved
collagen type III/I ratio when miR-29B is incorporated into the scaffold. Interestingly, this analysis
yielded some results that had minor discrepancy with the protein expression study results. The most
likely explanation for the opposing observations is that, in this study, wound healing gene expression
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Figure 4.14: An example heat map of gene expression data obtained from wound healing RT-
PCR array. Data presented is the upregulated (red) and downregulated (green) genes after 28
days when compared with healthy skin. Treatments analysed include No Treatment (wound
only) and treatment of wounds with a 1 mM 4S-StarPEG crosslinked collagen scaffold alone, or
a 1 mM 4S-StarPEG crosslinked collagen scaffold with 5 μg of miR-29B.
No Treatment No Treatment
Figure 4.15: Overview of number of genes altered in the different comparisons studied in the PCR array analysis with fold change cut off being five.
Data presented is the upregulated (red) and downregulated (blue) genes after 28 days when compared with healthy skin. Treatments analysed
include No Treatment (wound only) and treatment of wounds with a 1 mM 4S-StarPEG crosslinked collagen scaffold alone, or a 1 mM 4S-StarPEG
crosslinked collagen scaffold with 5 μg of miR-29B.
Col1a1 Col1a2 Col3a1 Tagln FGF2
Itga6
F3 FGA Actc-1
F13aI MMP-9 CCl12 F3 Itgb3 Serpine1 Cxcl5
Col3a1 Tagln Egfr Itga4
1 0
2 19
0
1
Gel Alone
No Treatment
Evalu
ation
of m
iR D
elivery
In V
ivo
No Treatment
Gel with 5 μg
miR-29B
2
22 1
Upregulated Genes
Downregulated Genes
Gel Alone
Gel with 5 μg
miR-29B
153
0
Evaluation of miR Delivery In Vivo
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regulation is not just occurring at the mRNA level. Gene expression can be controlled at the post-
transcriptional level by modulating the degradation rates of mRNA (as is the function of miRs)
and thereby increasing the number of proteins translated per mRNA molecule. It is possible that
there are other post-transcriptional controls that are still being unravelled, such as processes that
can increase/decrease the affinity between the desired mRNA and ribosomes 75
. It has been
observed that protein and mRNA transcript levels do not consistently correlate and that it is not
valid to assume that correlation implies causation in this context 76-78
. Based on this, it would be
appropriate to perform individual immunoblots such as Western blots (including appropriate
loading controls such as GAPDH) in future studies. Regardless, multiple genes were deregulated
when evaluated using PCR Array. The data is summarized in Figure 4.14 in a heat map format.
Notably, col1a1, col1a2, col3a1, col4a1 and col4a3 were downregulated in the scaffold with 5 μg
uncomplexed miR-29B compared to the scaffold alone. This is in agreement with numerous
reports that document a decrease in ECM gene transcription following delivery or overexpression
of miR-29B 6-8
. TGF-β1 gene expression remained unchanged between the samples and would
normally be expected that unchanged TGF-β1 expression correlates with an unchanged col1a1,
col1a2 and col1a3 gene expression, however, in the scaffold with 5 μg uncomplexed miR-29B
these genes were downregulated. This is because miR-29B silencing of these genes occurs post-
transcriptionally. Notably, the five-fold downregulation of the col1a1, col1a2 and col3a1 gene
expression was unique to the scaffold with 5 μg uncomplexed miR-29B.
4.4 Conclusions
In conclusion, multiple aspects of the remodelling response were evaluated in this study and from
these evaluations there was a significant impact when excisional wounds were treated with a a
scaffold alone, a scaffold with a dose of 0.5 μg uncomplexed miR-29B, 5 μg miR-29B;
uncomplexed or complexed with pD-b-P/DA. Any one of the treatments; scaffold alone or
scaffold with a dose of 0.5 μg miR-29B, or 5 μg miR-29B resulted in a significant reduction in
wound closure. Granulation volume fraction was greatest in the scaffold with 5 μg of
uncomplexed miR-29B treatment. This treatment did not have a significantly lower collagen type
III/I ratio when compared to native skin, and also had a statistically significant higher MMP-8:
TIMP-1 ratio when compared to all other treatments. The dose of miR-29B in the scaffold had an
effect in the majority of the parameters investigated. Two doses were investigated in this study;
uncomplexed 0.5 μg, and uncomplexed 5 μg, both uncomplexed, and both incorporated within a
scaffold. The use of the complexing agent; pD-b-P/DA, did not improve the effects of miR-29B
in wound remodelling, when assessed by the collagen type III/I ratios, granulation volume
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fraction and wound closure. Indeed the use of pD-b-P/DA complexed with 5 μg miR-29B in a
scaffold caused an upregulation of inflammatory cytokines when compared to 5 μg of
uncomplexed miR-29B in a scaffold. Notably, there was a significant correlation between the
dose of uncomplexed miR-29B when delivered through the scaffold and the ratio of MMP-8:
TIMP-1 which indicates that not only is the combination of these parameters important, but the
dose of miR-29B also has a significant effect on the parameters investigated. Through all the
investigations of this chapter it can be concluded that although a scaffold alone is beneficial
towards reduced wound contraction, incorporation of miR-29B in a dose dependent manner (in
this case 5 μg) ameliorates the wound healing process through modulation of MMP-8 and TIMP-
1, collagen type I degradation, and the post-transcriptional inhibition of ECM proteins which are
being stimulated by TGF-β1.
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|
Chapter Five
Summary and Future Directions
A portion of this chapter has been previously published in:
Monaghan M, Pandit A, RNA interference therapy via functionalized scaffolds. Adv. Drug Del. Rev. 2011, 63: 197-208.
MonaghanM, Greiser U, Wall J.G, O'Brien T, PanditA. Interference: An alteRNAtive therapy following acute myocardial infarction. Trends Pharmacol. Sci. 2012, 33: 635-645
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5.1 Introduction
Regenerative medicine aims to restore damaged tissue to its native structural and functional state.
While this goal may be overly optimistic, progress towards this goal will likely improve the outlook
for patients in a variety of disease and injury states. Simply reducing the extent of fibrotic scarring
will reduce the pathology in a number of conditions. This is unquestionably true in the case of
remodelling of cardiac tissue after myocardial infarction (MI). Gene therapy and biomaterials have
each been proposed for the treatment of damaged heart tissue in a variety of applications, ranging
from reducing inflammation, inducing angiogenesis, for functional reprogramming of cells, and to
mechanically augment the damaged tissue. The overall goal of this research was to develop a
biomaterial RNAi delivery system which inhibits fibrosis in a region of interest and thereby
improving the functional outcome in a pathological setting with the future objective being towards a
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SM, Marcucci G, Calin GA, Andreeff M, Croce CM. MicroRNA 29b functions in acute
myeloid leukemia. Blood. 2009;114:5331-5341 93. Aylon Y, Oren M. P53: Guardian of ploidy. Mol. Oncol. 2011;5:315-323
94. Vogelstein B, Lane D, Levine AJ. Surfing the p53 network. Nature. 2000;408:307-310
95. Park SY, Lee JH, Ha M, Nam JW, Kim VN. MiR-29 miRNAs activate p53 by targeting p85α and CDC42. Nat. Struct. Mol. Biol. 2009;16:23-29
96. Shi G, Liu Y, Liu T, Yan W, Liu X, Wang Y, Shi J, Jia L. Upregulated miR-29b
promotes neuronal cell death by inhibiting Bcl2l2 after ischemic brain injury. Exp. Brain Res. 2012;216:225-230
Summary and Future Directions
191
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192
A. Evaluation of miR-29B in a Myocardial Infarction Model
A.1. Introduction
Immediately following myocardial infarction (MI) a highly regulated process of cardiac
repair/remodelling follows the necrotic loss of cardiomyocytes beginning with the activation of latent
matrix metalloproteinases (MMPs) which degrade the existing extracellular matrix (ECM) and
coronary vasculature 1. This proteolytic activity declines by the end of week one post-MI and is
coincident with the increased expression of tissue inhibitors of MMPs (TIMPs) 2. Circulating
inflammatory cells (which include neutrophils and monocytes/macrophages) arrive at the infarct site
drawn by adhesion molecules and chemoattractant cytokines expressed by the endothelium of the
coronary vasculature bordering the infarct site. The penultimate fibrotic phase following MI
substitutes for lost parachymal cells following the initial phase of collagen degradation and begins
with the activation of transforming growth factor-β1 (TGF-β1), a key mediator of fibrosis. Increased
synthesis of fibrillar type III and type I collagens is present at week one post-MI and their organized
assembly in the form of scar tissue becomes evident at week two which continues to accumulate over
eight weeks 3. This excessive accumulation of ECM proteins in the interstitium and perivascular
regions of the myocardium during cardiac fibrosis is a hallmark of maladaptive hypertrophy and heart
failure 4. It causes the disruption of normal myocardial structures and increased mechanical stiffness,
which together contribute to contractile dysfunction of the heart. This fibrosis can also disturb the
electrical continuity between cardiomyocytes, leading to the impairment of conduction and facilitating
the occurrence of arrhythmias.
Fibroblasts are responsible for the turnover of ECM components, both in the healthy heart, as well as
in pathological fibrosis 5-6
. In the stressed myocardium, fibroblasts differentiate and become active
(termed myofibroblasts) in response to cytokines and growth factors such as TGF-β1 6. These
activated cells proliferate, migrate, and remodel the cardiac interstitium by modulating the secretion
of ECM components and MMPs. Signalling cascades that control ECM synthesis, ECM degradation,
and fibroblast proliferation and apoptosis involve SMADs, Rho/Rock, Elk-related tyrosine kinase-
mitogen activated protein (ERK-MAP), and P13K/Akt signalling pathways 6. Thus far, four
microRNAs (miRs) have been implicated in the regulation of cardiac fibrosis: miR-21, miR-29, miR-
30, and miR-133.
The Chapters Two, Three and Four have detailed the development and understanding of a tissue
engineering platform consisting of an atelocollagen type I hydrogel crosslinked using poly (ethylene
glycol) ether tetrasuccinimidyl glutarate (4S-StarPEG), a complexing agent; pD-b-P/DA and miR-
29B.
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193
As previously discussed, miR-29B has been specifically associated with the regulation of fibrosis in a
number of tissues including renal 7, bone
8, pulmonary
9, hepatic
10 and cardiac tissue
11. miR-29B
has also been elucidated to have a significant role in remodelling ECM tissue, possessing a significant
relationship with collagen production 11
. It has collectively been shown that the miR-29 family
members target at least 16 genes related to ECM which encode for several key proteins involved in
the physiological or pathological formation of extracellular matrix including; a large number of
fibrosis is stained blue/cyan and indicates the presence of proteoglycans. Scale bars indicate 1
mm.
miR-239B
miR-29B
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202
miR-239B miR-29B
200
400
600
800
Le
ft V
en
tric
ula
r W
all T
hic
kn
es
s (
m)
Figure A.4: Quantification of left ventricular wall thickness at 28 days following myocardial
infarction with miR-239B (negative control) or miR-29B treatment. No significant difference
was detected between groups at p < 0.05 using Student’s t-test. Data presented is the mean of n
= 6 ± standard deviation.
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203
Figure A.5: Fractional shortening % results obtained from echocardiographic data of animals
in groups with miR-29B or miR-239B (negative control) treatment. No significant difference
was detected between groups at p < 0.05 using Student’s t-test at each time point. Data
presented is the mean of n = 6 ± standard deviation.
Pre-MI 14 d post MI 28 d post MI
5
10
15
20
miR-239B miR-29B
Fra
cti
on
al S
ho
rte
nin
g (
%)
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204
Figure A.6: Left ventricular ejection fraction (LVEF) % results obtained from
echocardiographic data of animals in groups with miR-29B or miR-239B (negative control)
treatment. No significant difference was detected between groups at p < 0.05 using Student’s t-
test at each time point. Data presented is the mean of n = 6 ± standard deviation.
14 days post MI 28 days post MI
10
20
30
40
50
miR-239B miR-29B
LV
EF
(%
)
Appendices
205
earlier time point of 14 days and one at a much later time of 56 days which would reveal more
premature and more advanced remodelling respectively. Regardless, measurements were performed
on these micrographs to determine the effect of miR-29B on left ventricular wall thickness at 28 days
following MI (Figure A.4). Again, no statistically significant difference was observed between
animals treated with miR-29B (average wall thickness = 370 μm) and the negative control; miR-
239B. However, there was a trend towards a thicker left ventrical wall the myocardium from animals
treated with miR-29B (average wall thickness = 580 μm, Figure A.4) which suggests that there may
be less, or even still retarded remodelling occuring in this treatment group. Furthermore, there was
evidence of increased viable cardiomyocytes in the left ventricular wall of animals treated with miR-
29B but this observation was not statistically significant (Figure A.3).
A decreasing ratio of collagen type III to collagen type I is associated with reduced compliance of the
tissue, as observed in cardiomyopathy 34-35
. When the ratio of collagen type III/I was investigated in
this study it was found that while there were no significant changes in this ratio in the infarct, within
the border zone and also in the remote myocardium, there was a statistically significant decrease in
the collagen type I volume fraction in the group treated with miR-29B at the border zone area (Figure
A.6). This is somewhat reflected (although not significantly) in the collagen type III/I ratios (Figure
A.8) at the border zone where there is a trend towards an increased ratio in the miR-29B group in
comparison with the miR-239B control group (1.085 vs. 0.78, p = 0.14). This implies that the
infarcted tissue in these hearts was more elastic and less rigid than in the hearts treated with scaffold
alone. Improved elasticity of the infarcted area could explain the improvement in cardiac function in
these animals.
The infarct scar is composed of a population of fibroblast-like cells termed myofibroblasts (myoFb)
due to expression of α-SMA and resultant contractile behaviour 36-37
. These cells continue to turn over
type I and III fibrillar collagens long after scar tissue has restored the structural integrity of the
infarcted myocardium and are supported by a neovasculature. MyoFb collagen turnover is regulated
by substances including angiotensin II and TGF-β1 38-40
. The resultant fibrosis that appears over time
at sites remote to the infarct represents the majority of connective tissue found in ischemic
cardiomyopathy and is considered the major component of the adverse structural remodelling found in
the failing human heart of ischemic origin 41
. In this study, the expression of α-SMC was investigated
using immunofluorochemistry to determine the effect of miR-29B on the accumulation of myoFb that
may have derived from infiltrating stem cells 42
or differentiated fibroblasts 43
(Figure A.11). As
expected, an abundance of α-SMC expressing cell volume fraction was observed in the infarct area of
both the miR-239B control and miR-29B group (0.037 and 0.043) whereas less α-SMC expressing
cells were detected in the remote myocardium (Figure A.12). There was a trend (although this was not
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206
Figure A.7: Confocal micrographs of border zone, infarct and myocardium remote to the
infarct immunostained for collagen type I (green) and collagen type III (red) deposition using
immunoflurescent staining in cardiac sections from mice treated with miR-29B or miR-239B
(negative control). Sections are counterstained with DAPI (cyan). Scale bar indicates a length of
100 μm.
Border Zone Infarct Remote MyocardiummiR-239B(control)
Collagen I
miR-29BCollagen I
miR-239B(control)
Collagen III
miR-29BCollagen III
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207
Border Zone Infarct Remote Myocardium0.0
0.1
0.2
0.3
0.4
miR-239B miR-29B
*
Vo
lum
e F
rac
tio
n o
f C
olla
ge
n T
yp
e I
Figure A.8: Volume fractions of collagen type I obtained from confocal micrographs of cardiac
sections from mice treated with miR-29B or miR-239B (negative control). Data presented is the
mean of n = 6 ± standard deviation. * indicates a statistically significant difference between the
two groups indicated at p < 0.05, from Student’s t-test.
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208
Figure A.9: Volume fractions of collagen type III obtained from confocal micrographs of
cardiac sections from mice treated with miR-29B or miR-239B (negative control). Data
presented is the mean of n = 6 ± standard deviation. No statistically significant difference
between groups is detected using Student’s t-test, p < 0.05.
Border Zone Infarct Remote Myocardium0.0
0.1
0.2
0.3
0.4
0.5
miR-239B miR-29B
Vo
lum
e F
rac
tio
n o
f C
olla
ge
n T
yp
e III
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209
Border Zone Infarct Remote Myocardium0.0
0.5
1.0
1.5
2.0
miR-239B miR-29B
Ra
tio
of
Co
lla
ge
n T
yp
e III/I
Figure A.10: Ratio of volume fractions of collagen type III/I obtained from confocal
micrographs of cardiac sections from mice treated with miR-29B or miR-239B (negative
control). Data presented is the mean of n = 6 ± standard deviation. No statistically significant
difference between groups is detected using Student’s t-test, p < 0.05.
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210
Figure A.11: Micrographs of infarct and remote myocardium following treatment with miR-
29B or miR-239B (negative control). Sections are stained for α-SMA using immunoflurescent
staining (red) and counterstained with DAPI (cyan). Scale bar indicates a length of 200 μm
Appendices
211
Infarct Remote Myocardium0.00
0.02
0.04
0.06
0.08
miR-239B miR-29B
Vo
lum
e F
rac
tio
n o
f
-S
mo
oth
Mu
sc
le A
cti
n
Figure A.12: α-SMC volume fractions obtained from confocal micrographs of cardiac sections
from mice treated with miR-29B or miR-239B (negative control). Data presented is the mean of
n = 6 ± standard deviation. No statistically significant difference between groups is detected
using Student’s t-test, p < 0.05.
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212
Figure A.13: Micrographs of infarct and remote myocardium following treatment with miR-
29B or miR-239B (negative control). Sections are stained for TGF-β1 using immunofluorescent
staining (green) and counterstained with DAPI (blue). Scale bar indicates a length of 100 μm.
miR-29B
miR-239B
Infarct Remote Myocardium
Appendices
213
Figure A.14: Micrographs of infarct and remote myocardium following treatment with miR-
29B or miR-239B (negative control). Sections are stained using an in situ TUNEL kit for
apoptosis and counterstained with Mayer’s Haematoxylin. Arrow indicates an apoptotic cell.
Scale bar indicates a length of 20 μm.
miR-29B
miR-239B
Infarct Remote Myocardium
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214
Infarct Remote Myocardium0.00
5.00
10.00
15.00
20.00
miR-239B miR-29B
Mean
Nu
mb
er
of
Ap
op
toti
c C
ells/F
ield
Vie
w
Figure A.15: Quantification of number of apoptotic cells per field of view in the infarct and
remote myocardium following treatment with miR-29B or miR-239B (negative control). Data
presented is the mean of n = 6 ± standard deviation. No statistically significant difference
between groups is detected using Student’s t-test, p < 0.05.
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215
Figure A.16: In situ hybridisation using LNA oligonucleotides to detect miRs on formalin fixed
paraffin embedded sections. U6 is detection of U6 spliceosomal RNA. Scrambled LNA is
employed as a background control. Blue indicates the detection of RNA using LNA
oligonucleotides which is highlighted with arrows. Sections are counterstained with Nuclear
Fast Red. Rat myocardium has very low detection of miR-1 and U6 whereas human sections
have a higher detection.
Human Cervical Tissue U6 Human Myocardium U6
Rat Myocardium Scrambled LNA
Human Myocardium miR-1
Rat Myocardium U6
Rat Myocardium miR-1
Appendices
216
statistically significant) to an even more decreased occurrence of α-SMC cells in the remote
myocardium of animals treated with miR-29B compared with miR-239 control treated animals (0.006
vs. 0.01). Investigation of TGF-β1 expression revealed no difference between the administration of
miR-29B or miR-239B control (Figure A.13) neither within the infarcted myocardium nor in the
remote myocardium. In this study, one intervention was investigated; the sequence specificity of the
delivered miR. Therefore it can be presumed that no additional effects are observed as described in
Chapter Four, due to the simplicity of the intervention here. MI will itself elicit a dynamic response,
of which TGF-β1 plays a key role. Although the administration of miR-29B and miR-239B control did
not have any difference on the expression of TGF-β1 as described in this study; it is most likely that
miR-29B is silencing collagen type I (which was detected in the border zone of the infarcts, Figure
A.8), the production of which is being promoted by TGF-β1, post-transcriptionally.
Finally, it was sought to investigate the prevalence of apoptosis in cardiac tissue in response to the
administration of miR-29B or miR-239B control. The role of miR-29B on apoptosis has recently been
elucidated. For instance, miR-29B is known to have many targets, one of which is the anti-apoptotic
protein Mcl-1 44-46
. However, no significant apoptosis was noted in any of the sections stained in this
study, and in fact, apoptosis was in general, extremely low in both the infarcted myocardium and also
in the remote myocardium (Figure A.14 and A.15). Furthermore, apoptosis due to the event of
ischemia/reperfusion would not be detectable at this point 47
.
A.4. Conclusions
The results thus far presented are part of a pilot investigation to determine the therapeutic effect of
miR-29B as a modulator of fibrosis and maldaptive remodelling following myocardial infarction.
Given the study presented here, future investigations would warrant the employment of a robust
delivery vector to negate any degradation or rapid clearance of the miR-29B following tail-vein
injection. It has been reported that naked siRNAs and also siRNA in liposomal formulations, or mixed
with cationic reagents to improve their stability in vivo, become rapidy cleared from the bloodstream
by renal filtration within 5-30 minutes 48, 49
. To avoid this drawback, and indeed that of affecting
organs not intended to be affected, a more stable localised delivery approach is desired. This could
include consideration of a viral vector, such as an adeno-associated virus, which could be delivered
systemically and be engineered with a cardiac specific promotor 50, 51
.
Unfortunately the analyses of this pilot study have revealed that the study design was not powerful to
detect statistically significant differences for a number of the parameters investigated. However, some
conclusions may be made on the results obtained. The administration of miR-29B had a statistically
significant effect on the collagen type I deposition at the border zone of the infarcted myocardium and
this was also reflective in a strong trend towards an improved collagen type III/I ratio in the border
zone of the infarcted myocardium. Few conclusions can be made about the other parameters
Appendices
217
investigated as there exist no statistically significant differences. However, miR-29B had an apparent
trend towards an improvement on LVEF % which can be attributed to improved mechanical
compliance at the border zone of the infarct due to an increased collagen type III/I ratio. Finally, these
results provide an insight into further parameters to be investigated in future studies and highlight the
requirement of a localised delivery system to circumnavigate possible off-target effects and clearance
of a systemically delivered therapeutic.
The cardiac study was somewhat limited in its applicability. For example, a mouse heart weighs less
than a gram, while a human heart generally weighs more than 200 g. The difference in mass is
essentially correlated in the difference in the wall thickness (~ 1 mm vs. ~1 cm). The cellular
composition of the myocardium; however, do not differ, and thus the host response is somewhat
representative of the response a human heart would have to the treatment. Additionally, the MI model
in this study was created by ligating the LAD of an otherwise healthy animal. In humans, occlusion of
the coronary artery is a slow process, onset by underlying atherosclerosis, and present (in the majority
of cases) in individuals with sedentary lifestyles and unhealthy diets. Where possible, MI is treated by
reperfusing the affected tissue, an event which was simulated in this model.
The study was powered to detect changes in left ventricular ejection fraction (LVEF %) but not in
wall thickness or other histological parameters. The number of animals in each treatment group
should be at least ten to provide such power. Thus, there may have been changes in the histological
parameters that were not statistically significant due to the small sample size in this pilot study. It was
decided to investigate first the systemic delivery of miR-29B which is reported here. Intramyocardial
delivery is envisaged and is discussed in the Future Directions Section of this Thesis.
Appendices
218
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Appendices
221
B. Assessment In Vitro Using a Human Skin Equivalent Model
B.1. Introduction
In this Appendix in vitro evaluation of the scaffold functionalised with miR-29B and its effect on
wound closure in an in vitro human skin equivalent model, and also its influence effect on collagen
type I and collagen type III was investigated. The hypothesis tested was that the scaffold
functionalised with miR-29B, when applied to a human skin equivalent model will modulate the
healing response by reducing contraction of the wound and reduce collagen type I production.
Therefore, the objective was to investigate the effect of the components in this platform (miR-29B,
4S-StarPEG-collagen scaffold, pD-b-P/DA) on a number of key parameters involved in wound
healing, using a number of techniques. Specifically,
i. Evaluate, using histological analysis, wound closure following injury with a biopsy punch in
an in vitro human skin equivalent model .
ii. Quantify collagen type I and III deposition using immunohistochemistry.
B.2. Materials and Methods
B.2.1 Materials
All solvents were of analytical or HPLC grade and were obtained from Sigma Aldrich Chemical Co.
(Ireland) unless otherwise stated. All oligonucleotides and primers were purchased from Eurofins
MWG GmbH (Ebersberg, Germany). 4S-StarPEG was purchased from JenKem Technology USA
(Allen, TX, USA).
B.2.2 Complexation
miR-29B mimic was obtained from Qiagen (Hilden, Germany) with the sequences for rno-miR-29B:
5`-uagcaccauuugaaaucaguguu-3`; miRNA mimics were mixed individually with pD-b-P/DA at a w/w
ratio of 8:1 in 1 X phosphate buffered solution (PBS) as previously optimised in Chapter Two. The
components were mixed and complexes allowed to form at room temperature for 60 minutes.