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2Targeted delivery of miRNA
therapeutics for cardiovascular
diseases: opportunities and
challenges
Published in Clinical Science Vol. 126, No. 6, pp. 351-65, 2014Rick F. J. Kwekkeboom1,
Zhiyong Lei2,
Pieter A. Doevendans2,3,
René J. P. Musters1
Joost P. G. Slijter2,3
1 Department of Physiology, VU University Medical Center, Van der Boechorststraat 7,
1081 BT, Amsterdam, The Netherlands2 Experimental Cardiology Laboratory, Department of Cardiology,
Division of Heart and Lungs, University Medical Center Utrecht, P.O. Box 85500,
3508 GA, Utrecht, The Netherlands3 ICIN, Netherlands Heart Institute, Catharijnesingel 52, 3511 GC Utrecht,
The Netherlands
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Abstract
Dysregulation of miRNA expression has been associated with many cardiovascular diseases
in animal models, as well as in patients. In the present review, we summarize recent findings
on the role of miRNAs in cardiovascular diseases and discuss the opportunities, possibilities
and challenges of using miRNAs as future therapeutic targets. Furthermore, we focus on
the different approaches that can be used to deliver these newly developed miRNA thera-
peutics to their sites of action. Since siRNAs are structurally homologous with the miRNA
the rapeutics, important lessons learned from siRNA delivery strategies are discussed that
might be applicable to targeted delivery of miRNA therapeutics, thereby reducing costs and
potential side effects, and improving efficacy.
Key words: antimiR, cardiovascular disease, miRNA, siRNA, targeted delivery method
Abbreviations: ApoB, apolipoprotein B; AAV, adeno-associated virus; EC, endothelial cell,
i.v., intravenous; JNK1, c-Jun N-terminal kinase 1; LNA, locked nucleic acid; MB, microbubble;
PEI, polyethylenimine; PLGA, poly(lactic-co-glycolic acid); PLL, poly-L-lysine; RISC, RNA-
induced silencing complex; SHP-1, Src homology 2 domain-containing protein tyrosine
phosphatase-1; TLR, Toll-like receptor; US, ultrasound.
miRNA therapeutics for cardiovascular diseases
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miRNA BASICS
miRNAs are small regulatory non-coding RNA molecules 19–22 nucleotides in length, which
bind to the 3’-UTR region of mRNAs and regulate mRNA expression via degradation or inhi-
bition of their translation [1,2]. miRNAs are transcribed in the nucleus by RNA polymerase II,
like mRNAs, and are subsequently processed into a pre-miRNA by a combination of proteins
including the nuclear-located endonucleases Pasha and Drosha [3]. After being transported
out of the nucleus into the cytosol by ATPconsuming exportin-5 [4,5], pre-miRNAs are
processed further into mature miRNAs by the RNA endonuclease Dicer [6,7]. This step is
followed by the binding of RISC (RNA-induced silencing complex) [8], after which miRNAs
are ready to fulfil their inhibitory roles. The biogenesis and function of miRNAs have been
extensively discussed in previous work [9–14].
miRNAs IN CARDIOVASCULAR DISEASES
Over the last decade, miRNAs have been investigated extensively. In mammalians, they
are involved in many biological processes, if not all, including ESC (embryonic stem cell)
pluripotency [15], cellular proliferation [16–22], driving and directing differentiation [23,24],
regulating apoptosis [25,26], and aging [27–29]. The overall importance of miRNAs in the
cardiovascular system was established by knocking out key miRNA-processing components.
For example, cardiac-specific knockout of Dicer leads to dilated cardiomyopathy, heart
failure and eventually lethality in mice [30]. These Dicer-knockout mice have deregulated
cardiac contractile proteins and profound sarcomere disarray [30]. Similar to Dicer-knockout
mice, post-natal inactivation of Pasha in the heart leads to left ventricular malfunction,
dilated cardiomyopathy and lethality in adult mice [31]. The importance of miRNAs is not
limited to cardiomyocytes, since specific knockout of Dicer or Pasha in SMCs (smooth
muscle cells) leads to reduced proliferation and impaired contractility [32,33], and in ECs
(endothelial cells) to impaired post-natal angiogenesis [34]. Furthermore, specific miRNAs
were found to have pivotal roles in cardiovascular diseases, as has been explored exten-
sively in different animal models and is summarized in Figure 1. For example, Wang and
co-workers [35] and van Rooij co-workers [36] have shown that inhibition of dysregulated
miR-208 in pressureoverloaded hearts preserved cardiac function and reduced mortality.
In addition, when the heart is under stress, cardiomyocytes produce more ‘rubbish’, which
needs to be removed via autophagy. Ucar et al. [37] showed that misregulated miR-132/212
in the pressure-overloaded heart suppressed cardiomyocyte autophagy, which turned out
to be detrimental to cardiac function. Pharmaceutical inhibition of miR-132/212 rescued
the autophagic response and preserved cardiac function [37]. In another study, systemic
inhibition of miR-92a enhanced vessel growth and functional recovery of damaged tissue
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in a mouse hindlimb ischaemia model and myocardial infarction [38]. Similar results have
been reported in a large animal study in which inhibition of miR-92a reduced infarct size
and resulted in improved ejection fraction [39]. Owing to limited space, we refer to Table 1
and recent reviews for the role of individual miRNAs [13,40–43].
Figure 1: miRNAs involved in cardiovascular diseases. miRNAs are reported to be involved in many dif-
ferent types of cardiovascular diseases and in different cell types such as in angiogenesis for endothelial cells,
in cardiac fibrotic remodeling for myofibroblasts, and in proliferation, cell death, conduction and arrhythmias
for cardiomyocytes.
POTENTIAL OF mRNA THERAPEUTICS FOR CARDIOVASCULAR DISEASES
miRNA gain-of-functionAn advantage of miRNAs as potential therapeutic targets is their synergistic effects. miRNAs
bind to their targets in a partial complementary manner and increasing evidence suggests
that a single miRNA can target several genes within a similar signalling pathway [44,45].
The effect of a miRNA on an individual mRNA target sometimes is low, but, due to the
simultaneous regulation of multiple targets within a pathway, the combined effect is more
pronounced [45]. For example, miR-29 regulates the level of fibrosis through the direct
targeting of different collagens, fibrillins and elastins, which are all components of the
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extracellular matrix and collectively determine tissue stiffness, whereas each component
individually is only partly inhibited [46]. Therefore one advantage of using miRNA mimics is
the inhibitory effect they have on a selected pathway, by blocking several targets and lead-
ing to pronounced effects, both in vitro and in vivo. Another advantage of using miRNAs as
a therapeutic target is that their gain-of-function is easy to achieve by using miRNA mimics
or viral approaches. Depending on the vendor, the synthesized structure of miRNA mimics
varies, but they all have similar structures. The structure either resembles endogenously
present pre-miRNAs with a stem–loop or consists of a doublestranded RNA to help the
mimic get incorporated into RISCs. Many miRNA mimics have been shown to be functional
in vitro by numerous laboratories, including our own [19,47–
50]. miRNAs are relatively stable in the cell when compared with other RNA species, with
a half-life ranging from 28 h to 5 days, which is approximately 10 times longer than that of
mRNA molecules [51]. The long half-life of miRNAs indicates that potential miRNA mimics
may have long-lasting effects. van Rooij et al. [46] were among the first researchers who
tried to overexpress miR-29 mimics by systematic injection of cholesteroltagged miRNA
mimics at a dose of 80 mg/kg of body weight. They showed that there was a modest down-
regulation of miR-29-targeted genes, but this was accompanied by less fibrotic remodelling
[46]. Only a few in vivo applications of miRNA mimics can be found in the literature; however,
viral approaches, especially AAV (adeno-associated virus)-mediatedmiRNA gain-of-function,
are more widely used [52,53]. Owing to its low immunogenicity, the transgene can remain
active for months [53]. Eulalio et al. [53] used AAV9, a cardiac tropism of AAV serotypes,
to overexpress miR-590-3p and miR-199a-3p and showed a marked cardiac regeneration
aftermyocardial infarction [53]. The long-lasting high level of transgene expression make
AAVs an ideal tool for research, with potential future clinical applications.
miRNA inhibitionmiRNAs can be inhibited by synthetic miRNA inhibitors in vitro as well as in vivo [54].
The synthesis of miRNA inhibitors is even easier comparedwith miRNAmimics as they are
single-stranded. AntimiRs, widely used for in vitro studies, are chemically engineered single-
stranded oligonucleotides completely complementary to the 20-nucleotide-long targeted
miRNAs. To facilitate entry into the cell, antimiRs can be modified with cholesterol into a
so-called antagomiR [55].Upon systemic intravenous injection, this cholesterol-tagged an-
tagomiR can efficiently and specifically silence endogenous miRNAs throughout the body,
except for the brain [55]. miRNA inhibitors do not require incorporation into RISC to become
functional, but bind to endogenously present miRNAs and block their activities. This makes
it possible to modify their structure and thereby improve resistance to nucleases and speci-
ficity by increasing their affinity for the targeted miRNA. Several miRNA inhibitors have been
designed with different modifications at the 2’ position of the sugar molecule [55,56]. Among
these, 2’-MOE (2’-O-methoxyethyl) and 2’-fluoro modifications are the most commonly used
miRNA therapeutics for cardiovascular diseases
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[57–59]. Another type of modification, named LNA (locked nucleic acid) and using an O, 4’-C
methylene bridge to lock the furanose ring in the sugar-phosphate backbone, displayed
enhanced affinity for their targeted miRNA [60–65]. In fact, the LNA miRNA-binding affin-
ity is so high that tiny LNA molecules, complementary to only the 7-nucleotidelong seed
sequence of a family of miRNAs, can effectively block the wholemiRNA family [66]. The effect
of a single injection can last several months and this long-lasting inhibition of endogenous
miRNA targets probably originates from antimiRs having a different structure than natural
RNA species so that endogenous RNase cannot recognize them anymore.
CHALLENGES OF miRNA THERAPEUTICS FOR CARDIOVASCULAR DISEASES
miRNA gain-of-functionThe capacity to induce a long-lasting high level of transgene expression in combination with
low production cost makes the AAV an ideal tool for miRNA gain-of-function research [52,53].
However, the safety of AAVs in clinical applications is still under debate, and using viruses for
gene therapy still carries a negative connotation from failures in the past. It has been reported
that neutralizing antibodies against AAV virus can be detected in healthy populations [67],
and transgene products themselves can induce cell-mediated and humoral responses [68].
Besides, a definitive cardiac-specific serotype is not yet fully developed. For example, AAV9
is considered to be a cardiac tropism serotype [69–73]; however, AAV9 transgenes are also
expressed in other tissues, such as the liver and brain [68,74,75]. AAVs are promising and
further developments might well make them a successful clinical tool; however, the negative
public opinion regarding virus-based transgene delivery methods will most likely frustrate
developments. Even though miRNAmimics are powerful and widely used for in vitro studies,
in vivo delivery of miRNA mimics is challenging. Synthetic miRNA mimics, such as siRNA, have
a very short half-life in the blood [76]. As mentioned above, miRNA mimics have to be double-
stranded or need a stem–looped precursor structure so that they can be processed correctly
and functionally incorporated into RISC. This makes it difficult to modify their structure to
improve their stability, as with miRNA inhibitors, while maintaining their biological function.
Interestingly, endogenously expressed miRNAs are stable in serum for 4–6 years when stored
at −20 °C, whereas other RNA species are degraded [77]. These ‘circulating’ miRNAs may form
complexes with the miRNA effector protein Ago2 (Argonaute 2) [76], HDL (high-density
lipoprotein) [78], or can be incorporated into microvesicles, such as exosomes, microvesicular
bodies and apoptotic bodies, thereby being protected from RNase degradation [76,79]. On
the basis of these observations, it might be possible to improve the stability of miRNA mimics
in the circulation by forming complexes with protective proteins or polymers or loading them
into vesicles before injecting them into the body.
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miRNA inhibitionDifferent from miRNA mimics, miRNA inhibitors are already chemically modified RNA
molecules, which may be recognized by the body as foreign materials and thereby induce
inflammation, as is observed for siRNA [80]. It is well documented that foreign single- or
double-stranded synthetic siRNA can induce innate immune response through activation
of TLRs (Toll-like receptors) [80,81]. For instance, bacterial DNA or even mitochondrial DNA
fragments can induce inflammation through TLR9 signalling upon myocardial infarction
[82]. Although very useful, the high stability of miRNA therapeutics (antagomiRs and LNA)
is a double-edged sword. As we mentioned above, the effect of antagomiRs is very long-
lasting compared with conventional pharmaceuticals. With a single injection of antagomiR
at a dose of 80 mg/kg of body weight, inhibition of endogenous miRNAs can still be ob-
served after 1 month [37,52], probably due to a lack of nucleases that can recognize them in
mammalian cells. These long-lasting systemic effects of antagomiR or LNAwill increase the
chance of potential side effects in healthy regions or other organs of the body.
General challenges for miRNA mimics and inhibitorsBesides these specific challenges for miRNA mimics or inhibitors, there are some common
challenges for both of them. miRNA mimics and inhibitors are negatively charged. It is there-
fore difficult for them to leave the bloodstream and enter into the cell. Various delivery vehicles
have been used to help them enter into the cell, such as liposomes and polymers, which sig-
nificantly enhance cellular uptake and will be discussed below in more detail. However, 90%
of the mimics are still trapped in endolysosomal vesicles and cannot escape into the cytosol
of the cell [83]. Thus agents which can disrupt the endolysosomal compartments and help
them escape from endolysosome degradation, or new delivery techniques, are needed for
further development. A lack of effective organ-specific (e.g. cardiac-specific) delivery methods
is another problem for both miRNA mimics and inhibitors. In vivo administration of miRNA
mimics and inhibitors mainly relies on systemic injection, with related issues such as high
costs, potential side effects and low efficacy. It costs up to 250€ per mouse using antagomiR
with a dose of 80 mg/kg of body weight via systemic injection [84]. Given the body weight of
a human, it will cost more than 500000€ for a single treatment in humans. Even though lower
doses (<10 mg/kg of body weight) via repetitive injections [47] or using low-dose LNAs [66]
have been shown to be effective and cheaper, it will still cost approximately 100000€ for using
them in human trials. The cost may be reduced in the future with the development of synthe-
sis technology and more potent miRNA inhibitors. Another problem with systemic delivery of
miRNA therapeutics are the potential side effects. First, one miRNA can have multiple targets,
thus one miRNA may have different functions in different organs or cell types. For example,
miR-214 has been shown to play an inhibitory role in angiogenesis [59,85]; however, this
miRNA is also essential in regulating calcium homoeostasis in cardiomyocytes [86]. Therefore
systemic inhibition of miR-214 may improve neovascularization in the heart, but it may also
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cause problems in myocardial calcium handling. In summary, successful implementation of
miRNA therapeutics relies on strategies to improve the stability in the circulation, to reach
high efficient and tissue/cell-specific delivery, to have effective cellular uptake and eventually
to escape from the endolysosomal compartment.
OVERCOMING CHALLENGES: LESSONS LEARNED FROM siRNA DELIVERY
Several of the previously mentioned challenges for using miRNAs as therapeutic modalities,
both mimics and inhibitors, also apply when using siRNA as a therapeutic molecule. siRNAs
are double-stranded RNA-molecules 21–23 nucleotides in length that can be synthetically
produced. After cytosolic delivery they are incorporated into RISC like miRNAs. siRNAs have a
completely complementary sequence to their target mRNAs and binding of the siRNA–RISC
to their targets results in mRNA degradation [87]. As with miRNA mimics, siRNAs have similar
problems, such as being susceptible to degradation in the blood, not leaving the blood ves-
sels readily, and not readily being taken up by cells. To overcome these challenges, several
siRNA delivery vehicles, such as liposomal delivery vehicles, polymeric delivery vehicles
and US (ultrasound) MBs (microbubbles), have been studied. In order to overcome these
challenges for miRNA-based treatment, we can learn important lessons from these siRNA
delivery vehicles. An overview of these commonly used delivery vehicles is shown in Table 2.
Liposomal delivery vehiclesLiposomal are the most-studied and oldest delivery vehicle for siRNA, as reviewed recently
by Buyens et al. [88]. In the circulation, it has been shown extensively that liposomes protect
siRNA from RNase degradation and remain stable in the blood [88,89]. Additionally, Elbashir
et al. [90] have shown that cationic liposomes can induce the cellular uptake of siRNA in cell
culture through endocytosis, overcoming the challenge of low uptake of naked siRNA by cells.
Subsequently, cationic liposomes have been used to successfully treat liver metastasis in mice
by increasing apoptosis via targeting the bcl-2 oncogene in cancer cells [91]. Specific delivery
of an siRNA for CD31 to endothelial cells inhibited angiogenesis and decreased tumour growth
[92], thereby demonstrating that liposomes not only facilitate cellular uptake, but also assist in
the exit of siRNA from blood vessels into the tissue where they become biologically active in
vivo at several doses of 1–4 mg/kg of body weight. However, after i.v. (intravenous) injection,
siRNA-loaded liposomes tend to end up in the liver, kidney, lung, tumours, spleen and bone
[89,93,94], but not in the heart. Thus liposomes can solve major challenges for miRNA, antimiR
and siRNA delivery, including stability, cellular uptake and targeting of blood vessels or specific
organs, but still there is a need to increase delivery to the myocardium for cardiac applications
in order to improve therapeutic effects and avoid off-target side-effects.
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miRNA therapeutics for cardiovascular diseases
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Polymeric delivery vehiclesAnother strategy to overcome the challenges of siRNA delivery is the use of polymers, which
have been used with mixed successes [87,95,96]. There are many polymers that have been
used to improve siRNA delivery, and most commonly used are PEI (polyethylenimine), chitosan,
PLGA [poly(lactic-co-glycolic acid)], PLL (poly-L-lysine) and dendrimers. These polymers mostly
rely on their cationic charge to bind siRNA and subsequently protect siRNA from degradation
in the blood. Additionally, a cationic charge also induces endocytosis, thereby increasing cel-
lular uptake of the delivery vehicle. PEI was found to protect siRNA from RNase degradation in
the circulation and, after i.v. injection, siRNA ended up in tumours, liver, spleen, lung, kidney
and, to a low extent, in the heart of mice [97]. Indeed, tumour growth was decreased upon
i.v. treatment with a specific PEI–siRNA complex against VEGFR2 (vascular endothelial growth
factor receptor 2) [97]. Similarly, chitosan was found to protect siRNA from degradation for at
least 7 h, whereas naked siRNA is degraded within minutes upon systemic injection [98]. In
addition, after i.v. injection of an siRNA carrying chitosan in mice, the siRNA could be found
in the brain, liver, lungs, kidney, spleen, to a very low degree in the heart and abundantly
in tumours [99]. These delivered siRNA for POSTN (periostin), FAK (focal adhesion kinase) or
PLXDC1 (plexin domain containing 1) were subsequently capable of reducing tumour size
in mice [99]. Another polymer, PLGA, has been studied as an siRNA delivery vehicle because
it is FDA (Food and Drug Administration)-approved and provides a slow release of siRNA due
to the hydrolysis of PLGA [100], thereby making its therapeutic effects last longer. However,
PLGA is not cationic and is not readily taken up by cells, which makes loading PLGA with siRNA
more difficult and additional functionalities to improve cellular uptake have to be added [101].
If these additional functionalities are used, the resulting composite polymer is capable of
protecting an siRNA from degradation, enabling the exit of the siRNA out of the bloodstream
into tissue and subsequently inhibiting tumour growth [101]. Cardiac accumulation of these
particles, however, was not reported and, besides providing protection from degradation, the
challenges for siRNA delivery were not necessarily overcome by the characteristics of PLGA,
but rather by adding other polymers or moieties. PLL has been shown to deliver siRNA for
luciferase into cells, knocking down protein expression up to 80%in vitro [102]. However, when
trying to translate the use of PLL to in vivo models, several issues were encountered, such
as blood instability [103] and severe toxicity [102]. Additionally, PLL–siRNA delivery vehicles
mainly accumulate in the liver, spleen and tumours [104]. Dendrimers are branching polymers
and chemically challenging to produce [105]. For siRNA and oligonucleotide delivery, PPI
(polypropylenimine) or PAMAM [poly(amido amine)] have received most interest because of
their cationic nature [105]. Dendrimers have been proven to be able to cross cell membranes
and deliver siRNA intracellularly [106]. However, low dendrimer–siRNA stability in the blood
has been reported [107]. After i.v. injection, dendrimers are capable of transferring siRNA out
of the bloodstream after which they accumulate in the liver, kidney and spleen [106] or in
tumours after the addition of tumour-targeting functionalities such as a synthetic analogue of
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LHRH (luteinizing hormone-releasing hormone) [106], but no studies have reported specific
uptake and use in the heart. Several challenges have been conquered by using polymers to
deliver siRNA in vivo. This has resulted in successful therapeutic effects in laboratory animals
at several doses of siRNA, ranging from 1 to 3 mg/kg of body weight, whereas antagomiRs are
administered at 20–80 mg/kg of body weight. By using polymers such as chitosan, PEI and
PLGA it is possible to provide protection against degradation in the blood, and transfer the
siRNA out of the bloodstream and into cells to facilitate mRNA degradation. An overview of
the characteristics of discussed polymers is shown in Table 2. However, these siRNA–polymers
mostly end up in the liver, spleen, kidneys and tumours, and not in other organs such as the
heart, introducing the additional challenge of specifically targeted these delivery vehicles to
the myocardium.
Cardiovascular application of liposomal and polymeric delivery devicesAs mentioned above, liposomal and polymeric delivery vehicles for siRNA naturally accumulate
in tumours, the liver or spleen, and not in the vasculature and heart. Owing to this biodistribu-
tion, targeting the cardiovascular system with synthetic delivery vehicles is quite difficult. In
addition, the heart muscle is a difficult organ to transfect, and it is even believed that direct
injection of naked nucleotides results in higher cardiac uptake then nucleotides combined
with a delivery vehicle [108]. It has been hypothesized that the cationic nature of delivery
vehicles caused them to get attached to the densely packed anionic extracellular matrix of the
heart [109]. Even so, several approaches have been used to target the cardiovascular system
using siRNA delivery vehicles. To circumvent issues with biodistribution, delivery vehicles can
be directly injected into the myocardium [109–111] (Figure 2: delivery route 1). Kim et al. [109]
used a PEI-based delivery vehicle to deliver an siRNA against SHP-1 (Src homology 2 domain-
containing protein tyrosine phosphatase-1) to the myocardium of rats in an ischaemia/reper-
fusion model, resulting in a successful knockdown of SHP-1 and thereby reducing apoptotic
cell death and infarction size by 50% [109]. Alternatively, Somasuntharam et al. [111] used
pH-sensitive nanoparticles for intramyocardial siRNA delivery in a mouse modelwith a perma-
nent ligation in the left anterior descending coronary. As a result of Nox2 (NADPH oxidase 2)
knockdown, fractional shortening in the heart improved to non-infarcted myocardial levels
[111]. Additionally, direct injection of liposomes carrying miR-590 and miR-199 in the heart of
neonatal rats successfully increased cardiomyocyte proliferation within 3 days [53].
Even though biodistribution of cationic liposomes after i.v. injection does not favour the heart,
the i.v. approach to achieve cardiac effects has been reported (Figure 2: delivery route 2). For
instance, Santel et al. [112] successfully knocked down CD31 mRNA levels by 40%in the heart
after i.v. injection of liposomes loaded with siRNA in mice. CD31 is an EC-specific marker and
was used in that study to prove endothelial targeting of the delivery vehicle. Furthermore,
Betigeri et al. [113] used i.v. injection of liposomes, loaded with siRNA against JNK1 (c-Jun N-
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terminal kinase 1) to decrease apoptosis in the heart of mice during hypoxia, knocking down
JNK1 by 80% and significantly reducing apoptosis. Both studies report, however, that uptake
of liposomes in organs other than the heart is much higher [112,113]. Another approach to af-
fect the cardiovascular system is by indirect targeting via organs which are easier to transfect,
such as the liver [114,115] or spleen [116,117], which naturally show high accumulation of
delivery vehicles (Figure 2: delivery routes 3 and 4). In the liver, both PEI-based delivery vehicles
and liposomes were successfully used to knockdown ApoB (apolipoprotein B), resulting in a
reduction in serum cholesterol levels and thereby preventing atherosclerosis [114]. In another
approach, an siRNA against CCR2 (C-C chemokine receptor 2) was intravenously injected after
complexing with cationic liposomes. These liposomes accumulated in the spleen and trans-
fected monocytes, macrophages and neutrophils, leading to a lower responsiveness of these
cells to MCP-1 (macrophage chemoattractant protein-1), a chemoattractant which is released
from the infarcted heart. As a result, monocyte numbers in infarcted hearts were reduced
by 70%, which led to a 34% reduction in infarct size (Figure 2: delivery route 5) [116]. In a
follow up study, the same group found that the reduction in infarct size also leads to increased
left ventricular ejection fraction [117]. This approach was also used to decrease the number
Figure 2: Targeting the heart with siRNA delivery vehicles. Cardiac application of siRNA delivery ve-
hicles can occur via different application routes. Delivery strategies either rely on (1) intramyocardial injection
of siRNA-carrying delivery vehicles, or intravenous injection routes (2, 3, 4). After intravenous injection, delivery
vehicles can directly enter the heart (2) or enter off-target organs like the liver (3) or the spleen (4). Subsequently,
secondary effects of those organs can have therapeutic effects on atherosclerosis by reducing ApoB levels (3)
or by reducing monocyte chemotaxis (4). Reduced chemotaxis of monocytes from the spleen can also reduce
infarct size after myocardial infarction (5).
Chapter 2
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of macrophages and monocytes in atherosclerotic plaques, leading to an 82% reduction in
macrophages/monocytes in the plaque [116].
The main issue in treating the heart with siRNA remains the low accumulation of delivery
vehicles and siRNA. Although liposomal–siRNA formulations have entered the clinical arena
for treatment of cancer [118] and the liver [119], the heart still lags behind, creating a need
for improved cardiac homing of siRNA delivery vehicles. Interestingly, promising alternative
methods are being developed to treat myocardial infarction or atherosclerosis by targeting
organs such as the liver or spleen with subsequent effects on the heart, although these are
still in an early pre-clinical phase and mostly rely on a reduction in total cholesterol levels or
modulating the immune responses.
MicrobubblesMBs are micrometre-diameter gas-filled spheres with a flexible shell which can be modified
in order to bind nucleic acids such as DNA or siRNA [120–122]. The characteristic that makes
MBs really interesting as a drug delivery vehicle is their US responsiveness. Having a core of
gas, MBs react to US pressure waves. During the peak positive pressure phase, the gas-filled
MBs will be compressed and during the peak negative phase the MBs will expand, causing
the MBs to oscillate on the US wave. Increasing the peak-to-peak pressure of the US wave
to a certain point causes the MBs to collapse, thereby releasing the therapeutic payload
and permeabilizing cells [123,124] and blood vessels [125]. This results in an increased local
delivery and uptake of therapeutic payload if US is applied locally [126]. MBs have been used
for the local delivery of liposomes, nanoparticles, plasmid DNA and also siRNA [127].
MBs have been found to protect siRNA from RNase degradation in the circulation and for
transferring them out of the blood vessel into cells in tumour tissue, subsequently slow-
ing down tumour growth [120]. Similarly, Un et al. [128] used MBs to deliver siRNA against
ICAM-1 (intercellular adhesion molecule-1) to the liver and successfully delivered siRNA
in endothelial cells, Kupffer cells and hepatocytes, thereby providing protection against
ischaemia/reperfusion damage in the liver. MBs are therefore capable of protecting siRNA,
enable siRNA to exit the blood stream, and induce the entry of siRNA into cells.
Furthermore, the ability to use a physical force to induce local delivery makes the MB suit-
able to target tissues in which delivery vehicles do not naturally accumulate, and MB+US
has thereby been used to deliver siRNA or oligonucleotides to the heart [129,130]. In 2005,
Tsunoda et al. [130] successfully delivered siRNA against GFP in GFP transgenic mice. They
found that delivery was confined to the ECs in the heart [130] and was not observed in
cardiomyocytes, in contrast with delivery of plasmid DNA, which did enter cardiomyocytes
as well as ECs after MB+US treatment. Alter et al. [129] also showed that single-stranded
oligonucleotides could be delivered locally to the heart, inducing the transcription of
dystrophin in cardiomyocytes. Both studies showed successful delivery of small oligonucle-
otides to compartments of the heart while retaining biological activity without off-target
miRNA therapeutics for cardiovascular diseases
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effects in other organs. Although Tsunoda et al. [130] only found tissue penetration to ECs
by using double stranded siRNA, Alter et al. [129] observed tissue penetration reaching the
cardiomyocytes by using single-stranded oligonucleotides, which is an interesting differ-
ence between these RNA analogues.
MB+US-induced local delivery techniques look a promising approach for local miRNA
delivery in the cardiovascular system. Small RNA molecules are only delivered to organs
where US is applied and therefore the heart can also be reached, in contrast with the other
synthetic delivery vehicles discussed above. Penetration of siRNA into tissue, however, only
extends to ECs. For miRNA mimics, similar results can be expected as these molecules are
double-stranded as well. For antimiR molecules, being single-stranded, affecting both EC
cells and cardiomyocytes seems feasible. Although promising, MB+US-induced delivery of
siRNA is still rather complex and many factors are known to influence the success of local
delivery, including MB type [129], US intensity [131], US frequency [132], US pulsing [127]
and MB dose [129]. Furthermore, cavitating MBs can cause stress to blood vessels and cells
[121]. However, when all of these factors are well balanced, the MB+US-induced delivery
of miRNA mimics is a very promising technique for the treatment of cardiovascular disease,
including the myocardium.
IMPROVING CARDIAC DELIVERY
Strategies to improve the homing of delivery vehicles to the heart include the use of
antibodies,EC- or cardiac-targeting peptides, or pH-sensitive-targeting moieties. These
cardiac-targeting agents take advantage of distinct properties of cardiac tissue, such as
cardiac-specific cell-surface markers which can be recognized by antibodies or targeting
peptides. Ko et al. [133] used modified liposomes with a cell-penetrating peptide TATp for
increased cellular uptake and an anti-myosin antibody for cardiac targeting. This approach
resulted in increased accumulation of DNA–liposome complexes in the ischaemicmyocar-
dium [133]. Another well-studied targeting peptide is RGD that specifically binds to integrin
αvβ3 and αvβ5,which is enriched on the surface of ECs. This RGD peptide has been used
for targeted delivery of siRNA to ECs in combination with delivery vehicles such as chitosan
nanoparticles [99], PEI [134] and liposomes [135]. Using another approach, Sosunov et al
[136] reported that a low-pH-sensitive insertion peptide accumulates only in the ischaemic-
myocardium, but not in the healthy regions, as the pH in the ischaemic myocardium is
lower. These strategies improve cardiac homing, but have not been used in combination
with siRNA or miRNA therapeutics yet. It will be interesting to see how these promising
targeting strategies by themselves, or as a combination, improve cardiac homing of delivery
vehicles for siRNA and miRNA therapeutics.
Chapter 2
38
IMPROVING ENDOSOMAL RELEASE AND CYTOSOLIC DELIVERY OF miRNA THERAPEUTICS
Cellular entry of siRNA or miRNA therapeutics using delivery vehicles is usually endocytosis-
mediated, thus resulting in endolysomal localization. The last challenge for small RNA
therapeutic delivery after its entry into cells is release from its carrier and escape from the
endolysosomal compartment. To this end, fusogenic peptides have been used to facilitate
endolysosomal escape and improve cytosolic delivery of therapeutic molecules after inter-
nalization of drug delivery vehicles [137]. Hatakeyama and co-workers [138,139] showed that
the introduction of a pH-responsive fusogenic GALA peptide into a drug delivery vehicle
improved gene silencing due to more efficient endosomal escape. By combining fusogenic
peptides and cell-penetrating peptides, even more efficient knockdown has been achieved
[140,141]. Many protein/peptides such as GALA have been identified and can enhance
endosomal release, which can be considered for incorporation into the miRNA-therapeutics
delivery complex [142].
FUTURE PERSPECTIVES
miRNAs have been shown to play important roles in many different aspects of cardiovascu-
lar disease. Some properties that make the miRNA an excellent therapeutic target are the
ability to influence whole cellular processes instead of a single gene, the easy manipulation
of miRNA activity in vivo using miRNA inhibitors, the high intracellular stability of miRNA
therapeutics, and their involvement in regenerative processes in cardiovascular disease. Ac-
tually, the first successful Phase II clinical trial with antimiR-122 [143], a hepatitis C-targeting
antimiR, has been carried out and should definitely encourage the introduction of more
miRNA therapeutics towards clinical practice, and also potentially in the cardiovascular
field. However, the intrinsic nature of miRNAs targeting multiple target mRNAs can achieve
synergistic effects, but may also cause unexpected off-target side effects, since no organ- or
tissue selectivity is achieved, especially as the heart is difficult to reach. Moreover, in vivo
delivery of miRNA-mimicking molecules to enhance miRNA function is limited and is mainly
achieved by viral overexpression. There is therefore a persistent need for methods to in-
crease miRNA therapeutic delivery, prevent off-target uptake and increase tissue-specific
uptake. Recent developments in drug delivery vehicles for siRNA have resulted in success-
ful protection of siRNA in the blood, successful exit from the circulation and intracellular
delivery of siRNA, and important lessons can be learnt from these siRNA delivery methods.
Three important challenges have been conquered using liposomal and polymeric delivery
vehicles. However, the big issue remains that these delivery vehicles end up in tumours,
the spleen, liver and lungs, but not readily in the heart. For a cardiac application, one would
miRNA therapeutics for cardiovascular diseases
39
2
need high systemic doses of siRNA to reach therapeutic levels in the myocardium, resulting
in large off-target effects and low therapeutic benefit. Strategies to circumvent this problem
include local injection or indirectly treating the heart by targeting other organs with known
effects on the heart. However, local injections are invasive and targeting the immune system
is not cardiac-specific and can result in major side effects. An alternative approach is the use
of MBs and US, which are known to have low off-target effects. However, cardiac delivery
of siRNA by MB has not been studied extensively and data so far point towards low-tissue
penetration of siRNA. For a cardiac application of siRNA (or miRNA) therapy, cardiac target-
ing remains an issue. However, several strategies to improve cardiac uptake and targeting
of delivery vehicles are being developed, and encouraging results are being obtained with
antibodies, cardiac-targeting peptides and pH-sensitive-targeting peptides (for an overview
see Figure 3). These results, however, still need to be translated to delivery vehicles for miRNA
therapeutics. A growing body of knowledge is available, but this needs to be combined
with experimental and translational efforts to open up the successful delivery of miRNAs,
which are, at this point in time, the most potent therapeutic small RNA available.
Figure 3: Delivery vehicles for siRNA, targeting options and improving cytosolic delivery. Deliv-ery vehicles that can be used for siRNA delivery are represented in the left column, the size of the circles represents the size of the delivery vehicle. In the middle column, tissue targeting options which can be combined with delivery vehicles from the left column are depicted. Additionally, the right column gives an overview for options to increase cellular entry and endosomal escape.
Chapter 2
40
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