Inulin is a promising cryo- and lyoprotectant for PEGylated lipoplexes
Transcript of Inulin is a promising cryo- and lyoprotectant for PEGylated lipoplexes
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Journal of Controlled Releas
Inulin is a promising cryo- and lyoprotectant for
PEGylated lipoplexes
W.L.J. Hinrichsa,*, N.N. Sandersb, S.C. De Smedtb, J. Demeesterb, H.W. Frijlinka
aDepartment of Pharmaceutical Technology and Biopharmacy, University of Groningen, Antonius Deusinglaan 1,
9713 AV Groningen, The NetherlandsbLaboratory of General Biochemistry and Physical Pharmacy, Ghent University, Harelbekestraat 72, 9000 Ghent, Belgium
Received 2 November 2004; accepted 16 December 2004
Available online 15 January 2005
Abstract
The aim of this study was to investigate whether the oligosaccharides dextran and inulin are able to prevent aggregation of
lipoplexes based on 1,2-dioleoyl-3-trimethylammonium-propane and dioleoylphosphatidyl-ethanolamine with and without
distearoylphosphatidylethanolamine-polyethyleneglycol (PEGylated and nonPEGylated lipoplexes, respectively) during
storage. The lipoplexes, dispersed in the oligosaccharide solution were frozen and subsequently stored at subzero temperature
or freeze dried and subsequently stored at 37 8C. When lipoplexes in frozen dispersions were stored below the glass transition
temperature of the maximally freeze concentrated fraction (Tg’) of the oligosaccharide solutions severe aggregation of the
nonPEGylated lipoplexes was prevented for 3 months by both inulin and dextran. However, while dextran failed to stabilize the
frozen PEGylated lipoplexes (as in most cases full aggregation occurred in short time) inulin successfully protected them
against aggregation. Compared to dextran, inulin was also a superior lyoprotectant of PEGylated lipoplexes: during freeze
drying and subsequent storage at 37 8C of the dried powders for 3 months the PEGylated lipoplexes maintained their original
size when dispersed in inulin matrices while in dextran matrices they fully aggregated in most cases. It is hypothesized that the
aggregation of the PEGylated lipoplexes in dextran solutions is caused by the well known incompatibility between dextrans and
PEG. This is further supported by the observation that inulins and PEG are compatible. It is concluded that oligosaccharides can
prevent severe aggregation of nonPEGylated lipoplexes. The same holds for PEGylated lipoplexes provided that the
oligosaccharide is compatible with PEG. Finally, this work also shows that the higher Tg’ of oligosaccharides makes them more
versatile cryoprotectants than disaccharides like sucrose or trehalose as the frozen dispersions can be stored at higher
temperatures for prolonged periods of time. Furthermore, it is proposed that oligosaccharides are also more versatile
lyoprotectants than the disaccharides because they can be exposed to higher relative humidities without passing the glass
transition temperature.
D 2004 Elsevier B.V. All rights reserved.
Keywords: Freeze drying; Inulin; Lipoplex; Particle size; Stability
0168-3659/$ - s
doi:10.1016/j.jco
* Correspondi
E-mail addr
e 103 (2005) 465–479
ee front matter D 2004 Elsevier B.V. All rights reserved.
nrel.2004.12.011
ng author. Tel.: +31 50 363 3134; fax: +31 50 363 2500.
ess: [email protected] (W.L.J. Hinrichs).
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479466
1. Introduction
The elucidation of the human genome has boosted
the idea of using DNA as a therapeutic agent [1–3]. To
act as a therapeutic agent, DNA has to reach the
nucleus of the target cell. However, when DNA as
such is contacted with cells spontaneous introduction
of DNA in the nucleus hardly occurs. This limited
transfection efficiency can be partially ascribed to the
large hydrodynamic diameter and the negative charge
of DNA [4]. Moreover, considering in-vivo admin-
istration, many substances such as DNases are present
in the body, which metabolize the foreign DNA [4–6].
One way to solve these problems is to complex DNA
with cationic liposomes [7,8]. These lipid based gene
delivery systems, also known as lipoplexes, are
relatively small, neutral, or positively charged, and
protect DNA against degradation.
Lipoplexes are prepared in an aqueous environ-
ment, thus obtaining an aqueous dispersion. A major
drawback of these dispersions is their thermodynamic
driven tendency to lower their interfacial surface area
with the environment and thus to aggregate. Aggre-
gation strongly diminishes transfection [9]. This
physical instability is even more apparent when
during storage or shipping the dispersion is subjected
to freeze thaw cycles. At subzero temperatures, water
crystallizes through which the concentration of
remaining dispersion is strongly increased. By this
so-called freeze concentration the lipoplex particles
are forced towards each other through which aggre-
gation is facilitated.
Therefore, it would be advantageous to find a way
to prevent or at least slow down aggregation during
freezing. It would even be more advantageous to
prevent aggregation during freeze drying because,
once in a stable dry state, increased shelf lives can be
expected even at ambient temperatures. Having the
lipoplexes in the dry state would also offer the
possibility to develop dosage forms which are not
possible with aqueous dispersions e.g. tablets for oral
administration or dry powder formulations for pulmo-
nary delivery [10–12].
It is well known that sugars can stabilize a large
variety of unstable drug substances during freeze
thawing and freeze drying [13–16]. Furthermore, it
has been reported that lipoplexes can be stabilized by
sugars [17,18]. Stabilization has been explained by the
particle isolation hypothesis [19] and the vitrification
theory [20]. The particle isolation hypothesis refers to
the formation of a sugar matrix which acts as a
physical barrier between the lipoplex particles. The
vitrification theory refers to the formation of a glassy
sugar matrix in which diffusion on a realistic time
scale is inhibited. Both the physical barrier and lack of
translational movement prevent aggregation. To
ensure vitrification the sample temperature should be
below its glass transition temperature (Tg). Therefore,
for storage of aqueous dispersions at subzero temper-
atures or for freeze drying, sugars with a high glass
transition temperature of the maximally freeze con-
centrated fraction (Tg’) are preferred. Additionally,
also a high Tg (of the dry sugar) is beneficial for the
subsequent storage of powders obtained after freeze
drying. Storing the sample below the Tg is on the one
hand essential for vitrification. On the other hand, it is
important to maintain the particles isolated as above
the Tg the sugar is in the rubbery phase and
crystallization can occur. This crystallization will
force the particles towards each other. Therefore, it
is favorable when the sugar has a low tendency for
crystallization in case the Tg is (accidentally) passed.
A review of the literature reveals that especially small
sugars like the disaccharides sucrose and trehalose can
be successfully used for stabilization of lipoplexes
[19,21,22]. In contrast, polysaccharides like hydrox-
yethyl starch [19,21] and high molecular weight
dextrans [22] were found to act as poor stabilizers.
Based on the above described stabilization mecha-
nisms, this is rather unexpected because polysacchar-
ides usually have excellent physico-chemical
characteristics: besides a high Tg’ and Tg, they also
show a low tendency for crystallization compared
with disaccharides [23]. It has been hypothesized that
polysaccharides are too bulky to effectively incorpo-
rate the drug particles [21], i.e. the large molecules are
not able to accommodate to the surface of the lipoplex
and no tight coating can be obtained. This suggests
that oligosaccharides may be superior stabilizers since
they combine the advantageous properties of both
small saccharides and polysaccharides for optimal
stabilization of lipoplexes i.e. they have a high Tg’
and Tg, and low tendency for crystallization but are
small or flexible enough to effectively incorporate
lipoplexes. Indeed, in a preliminary study we have
found that the transfection efficiency of lipoplexes
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479 467
(based on 1,2-dioleoyl-3-trimethylammonium-pro-
pane/dioleoylphosphatidyl-ethanolamine liposomes
and plasmid DNA encoding for alkaline phosphatase)
freeze dried without additives was fully lost while
substantial transfection was observed when they were
freeze dried in the presence of oligosaccharides.
The aim of this study was to evaluate the effects
of oligosaccharides on the particle size and zeta
potential of lipoplexes during subzero temperature
storage and freeze drying followed by storage. It has
been reported that maintenance of particle size (and
zeta potential) is not the only determinant for
preservation of biological activity [20,24]. Treatment
may also induce structural changes in the tertiary
structure of plasmid which may affect the biological
activity but not particle size. However, determination
of particle size can be used as a screening method
because when severe aggregation of the lipoplexes
occurs, the transfection efficiency will always be
strongly diminished.
Four oligosaccharides were evaluated: inulin 1.8
and 4 kDa and dextran 1.5 and 5 kDa. Sucrose and
trehalose were used as positive controls and no sugar
and dextran 40 kDa as negative controls. Stability of
lipoplexes prepared with nonPEGylated and PEGy-
lated liposomes was considered. It can be envisaged
that during freeze thawing and freeze drying the
degree of compatibility of the oligosaccharide and
PEG will affect the stabilization of PEGylated lip-
oplexes by the oligosaccharide [25]. Therefore, in the
present work the compatibility of the oligosaccharides
with PEG was also studied and related to the extent
oligosaccharides prevent PEGylated lipoplexes from
aggregation.
2. Materials and methods
2.1. Materials
The lipids, 1,2-dioleoyl-3-trimethylammonium-
propane (DOTAP), dioleoylphosphatidyl-ethanol-
amine (DOPE), and distearoylphosphatidyletha-
nolamine-polyethyleneglycol (DSPE-PEG) with a
molecular weight of polyethylene glycol 2000 were
obtained from Avanti Polar Lipids (Alabaster, AL,
USA). Dextran 1.5 kDa and PEG 6 kDa were obtained
from Fluka (Zwijndrecht, the Netherlands). Dextran 5
and 40 kDa were purchased from Dextran Products
Limited (Scarborough, Ontario, Canada). Inulin 1.8
and 4 kDa (inulin types HD001111 and TEX!803,
respectively) were gifts of Sensus, Roosendaal, the
Netherlands. Plasmid DNA (pDNA) of 5803 base
pairs encoding the reporter gene secretory alkaline
phosphatase was used. The pDNA was amplified in
Escherichia coli, purified and dissolved in 20 mM
Hepes at pH 7.4 as previously described [9]. All other
chemicals were of analytical grade and purchased
from commercial suppliers.
2.2. Methods
2.2.1. Preparation of liposomes
Unilamellar nonPEGylated liposomes composed of
DOTAP/DOPE (molar ratio 1:1) and PEGylated
liposomes composed of DOTAP/DOPE/DSPE-PEG
(molar ratio 1:1:0.08) were prepared by the thin film-
extrusion method as reported previously [9]. Briefly,
appropriate amounts of lipids were dissolved in
chloroform in a round bottom flask. The solvent
was removed by rotary evaporation at 40 8C followed
by purging the flask with dry nitrogen for 30 min at
room temperature. The lipids were hydrated by adding
20 mM Hepes pH 7.4. Glass beads were added and
swirled around to facilitate detachment of the lipid
layer from the wall of the flask. Subsequently, the
formed vesicle dispersion was stored for 1 day at 4 8Cafter which it was extruded 11 times through two
stacked 100 nm polycarbonate membrane filters
(Whatman, Brentfort, UK) at room temperature.
2.2.2. Preparation of lipoplexes
Lipoplexes were prepared at +/� charge ratio of 4
(i.e. weight ratio DOTAP/pDNA of 8.5). A pDNA
solution of plasmid (in 20 mM Hepes at pH 7.4) was
added to a dispersion of liposomes (compositions see
above) and then vortexed for a few seconds as
described previously [9]. The final pDNA concen-
tration was 126 Ag/ml and the final lipid concentration
was 2.21 mg/ml (DOTAP/DOPE) or 2.46 mg/ml
(DOTAP/DOPE/DSPE-PEG).
2.2.3. Freeze thawing
From the lipoplex dispersions, as described above,
50 Al was added to 1.5 ml eppendorf cups and
subsequently either 50 Al of a sugar solution in water
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479468
(12.6 wt.%; thus final weight ratio sugar/plasmid was
1000) or 50 Al of pure water was added and shortly
vortexed. The resulting dispersions were frozen by
placing the samples in a refrigerator of �20 8C(sample temperature was decreased to below �15 8Cwithin 20 min) or �85 8C (sample temperature was
decreased to below �50 8C within 10 min). After 6
days, 1, or 3 months, the samples were rapidly thawed
by adding 0.9 ml Hepes (20 mM at pH 7.4) of room
temperature and then analyzed.
2.2.4. Freeze drying
From the lipoplex dispersions, as described above,
50 Al was added to 4 ml glass vials. Subsequently,
either 50 Al of sugar solution in water (12.6 wt.%; thus
final weight ratio sugar/plasmid was 1000) or 50 Al ofpure water was added and shortly vortexed. The
resulting dispersions were frozen by placing the glass
vials in a refrigerator of �85 8C (sample temperature
was decreased to below �50 8C within 10 min). After
16–24 h, the glass vials were placed in the freeze
dryer (Amsco-Finn Aqua GT4 freeze dryer) and
subsequently lyophilized at shelf temperature of
�35 8C, a pressure of 0.9 mBar for 2 h, and a
condensor temperature of �60 8C. Then, the shelf
temperature was raised to �15 8C while keeping the
pressure the same. After 13 h the pressure was
decreased to 0.15 mBar while the temperature was
gradually raised to 10 8C during 9 h. Subsequently,
the samples were removed from the freeze dryer.
Thus, freeze dried lipoplexes were either immediately
rehydrated with 1 ml Hepes (20 mM at pH 7.4) and
then analyzed or first placed in an oven at 37 8C for 6
days, 1, or 3 months. Furthermore, sugar solutions
(6.3 wt.%) in water and in Hepes (10 mM at pH 7.4)
were freeze dried according to a procedure described
before [23].
2.2.5. Determination of glass transition temperatures
Glass transition temperatures were determined by
calorimetric measurements using a 2920 differential
scanning calorimeter (DSC, TA instruments, Gent,
Belgium). The Tgs’ of sugar solutions (6.3 wt.%) in
water or in Hepes (10 mM at pH 7.4), and 10–200
mM Hepes buffer (at pH 7.4) were determined via the
following procedure. Solutions (40–50 Al) were
cooled to �60 8C with a cooling rate of 10 8C/min.
Subsequently, the samples were heated to 40 8C with a
rate of 20 8C/min. During these measurements, the
sample cell was purged with helium at a flow rate of
35 ml/min. The midpoint of the transition was taken
as the Tg’. Samples were measured at least in
duplicate.
Also the Tg of sugar glasses (with and without
Hepes) and of pure Hepes was measured. The sugar
glasses were prepared by freeze drying sugar solutions
(6.3 wt.%) in water or in Hepes (10 mM at pH 7.4).
The samples (5–10 mg) were preheated for 30 min at
40 8C (sucrose and trehalose containing samples) or
15 min at 90 8C (inulin or dextran containing samples)
subsequently cooled to 20 8C and then heated to 300
8C at a rate of 20 8C/min. The preheating step was
performed to remove moisture that was absorbed
during sample preparation. The Tg of pure Hepes was
determined as follows: crystalline Hepes (5–10 mg)
was heated to 250 8C (melting temperature of Hepes is
238 8C) and then rapidly cooled to 0 8C. Subse-
quently, the sample was heated at a rate of 20 8C to
100 8C. During the measurements, the sample cell
was purged with nitrogen at a flow rate of 35 ml/min.
The midpoint of the transition was taken as the Tg. All
samples were measured at least in duplicate.
2.2.6. Compatibility between oligosaccharides and
PEG
The compatibility between the oligosaccharides
and PEG was determined by two different procedures.
In the first procedure, which was adopted from Izutsu
et al. [26], the effect of oligosaccharides on the heat of
fusion of PEG hydrate in a frozen solution is
determined. When the compatibility between an
oligosaccharide and PEG increases, they will better
mix at subzero temperatures. Consequently, the
oligosaccharide will increasingly disturb crystalliza-
tion of PEG and thus the heat of fusion of PEG
hydrate will decrease. The heat of fusion was
measured as follows. Aqueous solutions of PEG 6
kDa (2 wt.%) and inulin 1.8 and 4 kDa or dextran 1.5,
5, or 40 kDa of various concentrations were eval-
uated. Trehalose and sucrose were used as controls.
DSC scans were performed in the DSC apparatus
described above. Solutions (40–50 AL) were cooled to
�60 8C with a cooling rate of 10 8C/min. Sub-
sequently, the samples were heated to 40 8C with a
rate of 20 8C/min. The heat of fusion of PEG 6 kDa
hydrate (at �14.5 8C [26]) was related to that of an
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479 469
aqueous solution of PEG 6 kDa (2 wt.%) without
additives. During the measurements, the sample cell
was purged with helium at a flow rate of 35 ml/min.
Samples were measured at least in duplicate.
In the second procedure to evaluate compatibility,
freeze dried powders were considered. Similar to what
has been described above, when a solution of PEG
and an oligosaccharide is freeze dried, crystallization
of PEG (anhydrate) is disturbed depending on the
degree of compatibility of both constituents. Again
this can be quantified by measuring heat of fusion of
crystalline PEG. Therefore, aqueous solutions of PEG
6 kDa (2 wt.%) and inulin 1.8 and 4 kDa or dextran
1.5, 5, or 40 kDa (all 5 wt.%) were freeze dried after
which the heat of fusion PEG 6 kDa anhydrate (at 60
8C) was related to that of a freeze dried aqueous
solution of PEG 6 kDa (2 wt.%) without additives.
The calorimetric measurements were conducted on the
same DSC apparatus as described above. The samples
(5–10 mg) were equilibrated for 2 min at 0 8C and
than heated to 100 8C with rate of 20 8C/min. The heat
of fusion of PEG 6 kDa anhydrate was related to that
of freeze dried aqueous solution of PEG 6 kDa (2
wt.%) without additives. During the measurements,
the sample cell was purged with nitrogen at a flow rate
of 35 ml/min. Samples were measured at least in
duplicate.
2.2.7. Particle size measurements
The Z-average particle size was determined by
dynamic laser scattering (DLS) using a Malvern 4700
system equipped with a helium-neon laser (Malvern,
Worcestershire, UK). For the data analysis, the
viscosity and refractive index of water were used. In
control experiments it was found that the presence of
sugars at concentrations used in this study did not
affect the results of the measurements (viscosity and
refractive index of the dispersing medium did not
change significantly). The performance of the instru-
ment was checked with polystyrene standard spheres
with a particle size of 220F6 nm (Duke Scientific,
Palo Alto, CA, USA). As a measure of particle size
distribution, the system reports a polydispersity index
(pd). This index ranges from 0 for a monodisperse
sample up to 1 for an entirely polydisperse sample.
All formulations were measured at least in duplicate
and each measurement consisted of five runs. In this
study a number of different batches of lipoplexes were
used which showed some variation in particle size.
Therefore, the size of the lipoplexes after a particular
treatment was expressed as percentage of the size of
the lipoplex of the same batch before treatment.
Samples were considered as bfully aggregatedQ whenone of the three following observations was made: (1)
large aggregates visible by eye, (2) a pd of 1 in more
than two out of the five runs, and (3) an increase in the
Z-average particle size by at least a factor three in
combination with an average pd higher than 0.9.
2.2.8. Zeta potential measurements
The zeta potential was measured by determining
the electrophoretic mobility using a Malvern zeta-
sizer 2000 unit (Malvern, Worcestershire, UK). The
zeta potential was calculated with the Smoluchowski
equation: f=12.8�le in which f is the zeta potential
and le is the electrophoretic mobility. The perform-
ance of the instrument was verified using a dispersion
of carboxyl modified polystyrene nanospheres with a
zeta potential of �50F5 mV (DTS5050, Malvern,
Malvern, UK). In control experiments it was found
that the presence of sugars at concentrations used in
this study did not affect the results of the measure-
ments (viscosity and refractive index of the dispersing
medium did not change significantly). In this study a
number of different batches of lipoplexes were used
which showed some variation in zeta potential.
Therefore, the zeta potential of lipoplexes after a
particular treatment was expressed as percentage of
the zeta potential of the lipoplex of the same batch
before treatment. All formulations were measured at
least in duplicate and each measurement consisted of
five runs. The zeta potential of samples that were
considered as fully aggregated (see above) was not
measured.
3. Results and discussion
3.1. Characteristics of starting materials
3.1.1. Glass transition temperatures
Aqueous sugar solutions and the corresponding
freeze dried sugars were analyzed by DSC (see Table
1). For sucrose and trehalose, Tgs’ of �30.7 and
�28.9 8C, respectively, were found which agree well
with literature values [27]. Substantially higher values
Table 1
Tgs’ (in 8C) of sugars solutions (6.3 wt.%) in water and in Hepes (10 mM at pH 7.4) and Tgs of the corresponding fried dried powders
Tg’ of the solution
in water
Tg’ of the solution
in Hepes
Tg of the
powder (water)
Tg of the
powder (Hepes)
Sucrose �30.7F0.1 �31.6F0.3 77.2F0.6 77.7F0.8
Trehalose �28.9F0.2 �30.4F0.1 120.9F0.5 119.7F0.1
Dextran 1.5 kDa �21.8F0.0 �23.2F0.2 152.5F0.4 147.0F0.1
Dextran 5 kDa �17.1F0.1 �18.5F 0.0 175.6F3.1 171.9F1.1
Dextran 40 kDa �11.9F0.1 �13.6F0.1 226.6F0.7 214.0F0.1
Inulin 1.8 kDa �21.2F0.2 �22.6F0.1 132.9F0.1 130.7F0.6
Inulin 4 kDa �17.8F0.1 �19.3F0.2 156.9F0.9 151.9F1.2
Pure Hepes b�60 8C 52.6F1.5
Table 2
Particle size and zeta potential of liposomes and lipoplexes
Particle
size
in nm
pd Zeta
potential
in mV
Liposome DOTAP/DOPE 124F5 0.12F0.03 43F9
Liposome DOTAP/DOPE/
DSPE-PEG
124F8 0.11F0.02 24F8
Lipoplex DOTAP/DOPE 227F24 0.16F0.04 47F5
Lipoplex DOTAP/DOPE/
DSPE-PEG
195F28 0.13F0.08 14F4
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479470
were found for inulin as well as for dextran.
Furthermore, in accordance with the Fox–Flory theory
[28–31], the Tg’ increased with molecular weight for
both inulin and dextran. As described above, lip-
oplexes were dispersed in sugar solutions (6.3 wt.%)
containing 10 mM Hepes at pH 7.4. Therefore, the
Tgs’ of sugar solutions (6.3 wt.%) in Hepes (10 mM
at pH 7.4) were also measured. As can be seen in
Table 1, the presence of Hepes lowers the Tg’ of the
sugars in all cases. A change in the Tg’ can be
ascribed to the incorporation of buffer species in the
maximally freeze concentrated fraction [32]. A
decrease of the Tg’ indicates that the Tg’ of a pure
buffer solution is lower than that of the pure sugars
solutions. Indeed DSC scans from �60 8C to 40 8C of
Hepes solutions with concentrations up to 200 mM
showed no Tg’ indicating that the Tg’ is lower than
�60 8C.The Tg of the freeze dried sugars showed a similar
trend (see Table 1): the Tg increased in the order
sucrose, trehalose followed by both oligosaccharides
inulin and dextran. Again in accordance with the Fox–
Flory theory [29,31], the Tg of the oligosaccharides
increased with molecular weight. The values found
correspond well with literature values [23,30,33,34].
Also the Tgs of freeze dried sugar solutions (6.3
wt.%) prepared in Hepes (10 mM at pH 7.4) were
determined. They were lower than the corresponding
freeze dried sugar solutions prepared in pure water
(except for sucrose). Furthermore, a Tg of pure Hepes
was found to be 52.6 8C. These results indicate that
Hepes forms homogeneous mixtures with each of the
sugars which is in agreement with the observation that
Hepes is incorporated in the maximally freeze
concentrated fractions.
3.1.2. Size and zeta potential of the liposomes
In this study eight batches of each liposome
composition (DOTAP/DOPE and DOTA/DOPE/
DSPE-PEG) were independently prepared. Table 2
shows that the particle size was highly reproducible
and averaged at about 125 nm. The liposome
dispersions also had a low polydispersity as the pd
was 0.11–0.12 (see Table 2). The zeta potential of the
DOTAP/DOPE liposomes (43 mV) was substantially
higher than that of the DOTA/DOPE/DSPE-PEG
liposomes (24 mV). The decrease of the zeta potential
by the incorporation of DSPE-PEG was expected and
can be ascribed to two different mechanisms. First,
DSPE-PEG contains a negative charge decreasing the
zeta potential. Secondly, the PEG chains increased the
distance between the surface of the liposome and the
plane of shear through which the positive charge is
increasingly neutralized by ions present in the
dispersion medium [35].
3.1.3. Size and zeta potential of the lipoplexes
Lipoplexes were prepared at a +/� charge ratio of
four by complexing the liposomes with pDNA at a
-60 -40 -20 0 20 40
Temperature (°C)
Hea
t fl
ow
(ex
oth
erm
up
)
CrystallizationPEG hydrate Melting
PEG hydrate
Melting H2O
Fig. 1. DSC scan of 2 wt.% solution of PEG 6 kDa in water.
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479 471
lipid/pDNA weight ratio of 17.5. In this study fifteen
batches of each type of lipoplexes (i.e. nonPEGylated
and PEGylated lipoplexes) were independently pre-
pared. As can be seen in Table 2, particle size analysis
showed some interbatch variation. Upon complex-
ation the liposomes increased in size. Such an increase
is usually found and indicates that the lipoplex
contains more than one of the original liposomes
[36]. The zeta potential of the nonPEGylated lip-
oplexes did not differ significantly from the zeta
potential of the nonPEGylated liposomes. This indi-
cates, as also observed by others, that the plasmid
DNA became sandwiched between two lipid
(bi)layers [9,37]. On the other hand, the slight
decrease in the zeta potential of the PEGylated
liposomes upon DNA complexation indicates that at
least part of the plasmid DNA becomes bound to the
surface of the lipoplexes. Finally, gel electrophoresis
did not reveal free plasmid DNA in both the
nonPEGylated and PEGylated lipoplexes (data not
shown).
3.2. Compatibility between oligosaccharides and
PEG
Besides the Tgs’ and Tgs of the sugar solutions and
freeze dried sugar solutions, respectively, the stabili-
zation of especially PEGylated lipoplexes may also be
dependent on the compatibility of the sugar and PEG.
The compatibility between the sugars and PEG was
characterized by measuring the effect of sugars on the
heat of fusion of PEG hydrate in frozen solutions and
the heat of fusion of PEG anhydrate in freeze dried
solutions.
It is well known that dextran and PEG are
incompatible in an aqueous solution i.e. when a
concentrated aqueous dextran solution is added to a
concentrated aqueous PEG solution, the system forms
two phases, one rich in dextran and the other rich in
PEG [38,39]. At low concentrations, dextran and PEG
can form homogeneous solutions in water. However,
when such a solution is frozen the concentration of
both solutes in the freeze concentrated fraction is
strongly increased (by ice formation) which may
result in phase separation [26,40–42]. The degree of
phase separation can be quantified as follows. When a
solution of PEG in water is rapidly cooled and then
heated in a DSC pan, the following observations can
be made. At around �45 8C an exothermic peak is
observed followed by two endothermic peaks around
�14.5 and 4 8C (see Fig. 1). These thermal events can
be ascribed to the crystallization of PEG-hydrate and
the fusion of PEG-hydrate and the fusion of water,
respectively. When an oligosaccharide, which is
compatible with PEG, is added to the solution and
the same DSC scan is performed, both solutes remain
mixed during freeze concentration. As a result, the
oligosaccharide is able to disturb the formation of
PEG-hydrate upon heating. Consequently, both the
heat of crystallization at �45 8C and the heat of fusion
at �15 8C will decrease. These changes will be more
pronounced with increasing oligosaccharide concen-
tration. In contrast, when the added oligosaccharide is
incompatible with PEG, the freeze concentrated
fraction will separate in two different phases, one
rich in PEG and the other one rich in oligosaccharide.
Being predominantly present in another phase, the
oligosaccharide is unable to disturb the formation of
PEG-hydrate crystals. Consequently, the heat of
crystallization at �45 8C as well as the heat of fusion
at �15 8C will not decrease or decrease to a lesser
extent.
Aqueous solutions of 2 wt.% PEG 6 kDa and
sugars of various concentrations were evaluated.
Sucrose and trehalose were used as controls because
it has been reported that these disaccharides are
compatible with PEG [26]. The results confirm this
compatibility as crystallization of PEG was fully
inhibited at a sucrose or trehalose concentration of
already 2.5 wt.% (see Fig. 2). As expected the results
show that dextran and PEG are highly incompatible
as the heat of fusion of PEG hydrate remained
substantial at dextran concentrations up to 10 wt.%.
In contrast, both inulins strongly disturbed crystal-
020406080
100120140
0 2 4 6 8 10 12
[sugar] in wt-%
Hea
t o
f fu
sio
n o
fP
EG
hyd
rate
(%
)
Fig. 2. Effect of sugars on the crystallization of 2 wt.% PEG 6 kDa
in frozen solutions. Sucrose (o), trehalose (5), inulin 1.8 kDa (4),
inulin 4 kDa (w), dextran 1.5 kDa (.), dextran 5 kDa (n), and
dextran 40 kDa (E).
020406080
100120
inulin
1.8
kDa
inulin
4 kD
a
dextr
an 1
.5 kD
a
dextr
an 5
kDa
dextr
an 4
0 kD
aCry
stal
linit
y P
EG
(%
)
Fig. 3. Effect of sugars on the degree of crystallinity of PEG 6 kDa
after freeze drying of a solution of 5 wt.% sugar and 2 wt.% PEG 6
kDa as calculated from the heat of fusion measured by DSC.
O
CH2OH
HH
OH
OH
H
H
OH
HO
O
OH
OHCH2OH
H
H
HCH2
O
O
OH
OH
CH2OH
H
H
HCH2
O
O
OH
OHCH2OH
H
H
HCH2OH
n
C
C
C
Fig. 4. Structure of inulin with emphasis on its PEG-like backbone
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479472
lization of PEG. In fact, the extent of crystallization
inhibition by inulins and disaccharides was compa-
rable (see Fig. 2), indicating that inulin and PEG are
fully compatible.
In the second procedure to evaluate compatibility,
freeze dried samples were considered. When using
most lyophilizators, PEG crystallizes (as an anhydrate)
during freeze drying. This is due to the fact that the
sample temperature is usually higher than the Tg’ of
PEG (�85 to �65 8C, depending on its molecular
weight [43]). Crystallization is manifested by an
endothermic (melting) peak in a DSC scan at 65–70
8C or lower depending on the molecular weight of
PEG. Similar to what has been described above, when a
solution of PEG and an oligosaccharide is freeze dried,
crystallization is disturbed depending on the degree of
compatibility of both constituents. Again this can be
quantified by measuring heat of fusion of crystalline
PEG. The heat of fusion of PEG of freeze dried aqueous
solutions of PEG 6 kDa (2 wt.%) and dextran or inulin
(5 wt.%) was determined and related to the heat of
fusion of a freeze dried aqueous solution of PEG 6 kDa
(2 wt.%) without additives. The incompatibility of
dextran and PEG was evident as the crystallinity of
PEG was 80–100% compared to PEG freeze dried
without additives (see Fig. 3). Furthermore, these
experiments showed that inulin and PEG are compat-
ible as the crystallinity of PEG was below 20%
compared to PEG freeze dried without additives.
As the phase behavior of polymer mixtures is a
delicate issue, we can only hypothesize at this point,
why in contrast to dextran, inulin is compatible with
PEG. One way to approach this question is to
compare their structural characteristics. It is well
known that compatibility increases when oligomers
are more alike [38]. When the structures of inulin and
PEG are considered, two characteristics attract atten-
tion because they point to similarities. First of all, both
oligomers are highly flexible when dissolved in water
[44]. Although many factors play a role, in many
cases polymers are compatible when they have
comparable flexibilities [38]. Secondly, the molecular
structure of inulin closely resembles PEG since it
consists of a PEG backbone with sugar moieties as
side groups (see Fig. 4).
3.3. Stability of lipoplexes
3.3.1. Effects of storage at �20 8C on particle size of
lipoplexes
The effects of various sugars on the aggregation
behavior of nonPEGylated and PEGylated lipoplexes
upon storing the frozen dispersions at �20 8C were
evaluated. This temperature was chosen because
.
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479 473
freezers at �20 8C belong to standard laboratory
equipment. The results are summarized in Fig. 5a and
b. Without sugars nonPEGylated lipoplexes severely
aggregated already within 6 days of storage indicating
the necessity of using a cryoprotectant (see Fig. 5a). In
the presence of the sugars investigated in this study,
no matter which one, severe aggregation did not occur
within 6 days of storage as the particle size only
increased to 125–150% of its original value. However,
at prolonged storage (1 or 3 months) sucrose and
trehalose were not able to prevent severe aggregation.
These results can be explained by the Tgs’ of these
sugars (see Table 1), which are much lower than the
storage temperature. During the lowering of the
temperature to �20 8C substantial freeze concentra-
tion will occur. However, at �20 8C the concentrated
solution is not yet in its glassy but in its rubbery state.
Because the lipoplexes are closer in each other’s
vicinity (the volume of the freeze concentrated
fraction is smaller) and because diffusion is possible,
aggregation is facilitated. In addition, above the Tg’
sugars can crystallize through which the lipoplexes
0
100
200
300
a
b
no e
xcipi
ent
sucr
ose
treha
lose
inulin
1.8
kDa
inulin
4 kD
a
dextr
an 1
.5 kD
a
dextr
an 5
kDa
dextr
an 4
0 kD
apar
ticl
e si
ze (
%)
0
100
200
300
no e
xcipi
ent
sucr
ose
treha
lose
inulin
1.8
kDa
inulin
4 kD
a
dextr
an 1
.5 kD
a
dextr
an 5
kDa
dextr
an 4
0 kD
apar
ticl
e si
ze (
%)
Fig. 5. Particle size, as percentage of the value before storage, of
nonPEGylated (a) and PEGylated (b) lipoplexes after storage at
�20 8C of the frozen dispersions for 6 days (n), 1 month ( ), and 3
months ( ). Severely aggregated lipoplexes are indicated by bars
that pass the upper axis.
are forced together which also promotes aggregation.
According to Allison et al. [21] vitrification is not a
prerequisite for maintenance of particle size during
freeze thawing. However, they stored the frozen
dispersions only for one night at subzero temper-
atures. Therefore, these published results are not in
contradiction with our results since we also observed
no substantial aggregation of the lipoplexes dispersed
in sucrose or trehalose within 6 days but after
prolonged storage times.
When dispersed in a solution of dextran 1.5 kDa,
the nonPEGylated lipoplexes also substantially
increased in size after 1 and 3 months of storage.
Again this can be ascribed to the state of the freeze
concentrated sugar solution: the Tg’ of this solution is
a few degrees below storage temperature, however, a
glass transition concerns a gradual change in molec-
ular mobility over a certain temperature range rather
than an abrupt change at a fixed temperature. This
implies that at �20 8C, the mobility of the lipoplexes
may still be significant though reduced. In addition
dextran 1.5 kDa, being an oligosaccharide, will not
crystallize as easily as small sugars like sucrose and
trehalose. Considering these facts, aggregation is
indeed expected to occur but not at such a high rate
as observed with sucrose and trehalose.
Dispersed in an inulin 1.8 kDa solution the particle
size of nonPEGylated lipoplexes remained the same
after 3 months of storage. Similar to the dextran 1.5
kDa solution, the Tg’ of the inulin 1.8 kDa solution is
a few degrees below storage temperature. Possibly,
the glass transition of the inulin 1.8 kDa solution
covers a broader temperature range and translational
movements are already very restricted at �20 8C. Theparticle size of nonPEGylated lipoplexes frozen in the
presence of dextran 5 kDa, dextran 40 kDa, or inulin 4
kDa did not change after 3 months of storage at �20
8C. These solutions have Tgs’ above �20 8Cemphasizing the importance of storing the dispersions
in the glassy state. Remarkably, dextran 40 kDa,
which was due to its bulky nature considered as a
negative control [22], also exhibited sufficient cry-
oprotective properties to prevent aggregation.
Due to their steric repulsion effect PEGylated
particulate systems are generally more stable than
their nonPEGylated counterparts [18]. However, as
also found by Armstrong et al. [45], PEGylated
lipoplexes still require cryoprotectants as a PEGylated
0
50
100
150
200
no e
xcipi
ent
sucr
ose
treha
lose
inulin
1.8
kDa
inulin
4 kD
a
dextr
an 1
.5 kD
a
dextr
an 5
kDa
dextr
an 4
0 kD
a
par
ticl
e si
ze (
%)
0
50
100
150
200
no e
xcipi
ent
sucr
ose
treha
lose
inulin
1.8
kDa
inulin
4 kD
a
dextr
an 1
.5 kD
a
dextr
an 5
kDa
dextr
an 4
0 kD
a
par
ticl
e si
ze (
%)
(a)
(b)
Fig. 6. Particle size, as percentage of the value before storage, of
nonPEGylated (a) and PEGylated (b) lipoplexes after storage a
�85 8C of the frozen dispersions for 6 days (n), 1 month ( ), and 3
months ( ). Severely aggregated lipoplexes are indicated by bars
that pass the upper axis.
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479474
lipoplex dispersion without excipients fully aggre-
gated within 6 days when stored at �20 8C (see Fig.
5b). Similar to the results on nonPEGylated lip-
oplexes, sucrose, trehalose, and both inulins were able
to prevent severe aggregation of PEGylated lipoplexes
stored at �20 8C for 6 days as the particle size
increased with only 25–50%. With dextran 1.5 kDa,
however, substantial aggregation occurred while with
both dextrans of higher molecular weight full aggre-
gation was observed within 6 days at �20 8C.Upon prolonged storage at �20 8C, PEGylated
lipoplexes dispersed in sucrose and trehalose strongly
increased in size but in a lower rate than non-
PEGylated lipoplexes under similar conditions. Again
the aggregation is due to the fact that Tgs’ of the
solutions are lower than the storage temperature while
the lower rate of aggregate formation can be ascribed
to steric stabilization caused by PEGylation. Dis-
persed in both inulin solutions, the size of PEGylated
lipoplexes was more or less maintained although some
aggregation was noticed with the inulin 4 kDa
containing samples after 3 months of storage at �20
8C. Given the relatively large SD, the anomalous
behavior of the inulin 4 kDa containing samples after
storage for 3 months is probably due to experimental
errors. Dispersed in the three dextran solutions,
PEGylated lipoplexes fully aggregated within 1 month
of storage at �20 8C.Clearly, in contrast to nonPEGylated lipoplexes,
Tg’ of the dispersion medium is not the only factor
that determines aggregation behavior of PEGylated
lipoplexes during subzero temperature storage. Inter-
estingly, these results can be related to the (in)com-
patibility of the oligosaccharides and PEG i.e. it seems
that oligosaccharides can prevent severe aggregation
of PEGylated lipoplexes on the condition that the
oligosaccharide is compatible with PEG. The follow-
ing mechanism can be proposed. When a dispersion
of PEGylated lipoplexes in a dextran solution is
frozen, the concentration of both lipoplex and dextran
is strongly increased by ice formation. As a result, the
dextran molecules tend to penetrate the PEG shell
surrounding the particles. However, as they are
incompatible, dextran will diffuse away from the
PEG shell thereby forcing the lipoplex particles
together leading to aggregation. Such a process can
be compared with the phase separation during freeze
concentration of dilute aqueous solutions of PEG and
dextran. It has been reported that the degree of
incompatibility increases with molecular weight
[39]. This is indeed reflected in the fact that the
cryoprotective activity of dextran 5 and 40 kDa is
worse than that of dextran 1.5 kDa. This hypothesis is
confirmed by the fact that inulins are compatible with
PEG and indeed these oligosaccharides behaved as
excellent cryoprotectants for PEGylated lipoplexes.
3.3.2. Effects of storage at �85 8C on particle size of
lipoplexes
The effects of various sugars on the aggregation
behavior of nonPEGylated and PEGylated lipoplexes
were also evaluated upon storing the dispersions at
�85 8C. The results are summarized in Fig. 6a and b.
It appeared that also upon storage at �85 8C,nonPEGylated lipoplexes dispersions fully aggregated
within 6 days when dispersed in pure buffer solution
(see Fig. 6a). In contrast, all sugars under inves-
tigation were able to prevent severe aggregation of
nonPEGylated lipoplexes during storage up to 3
months at �85 8C. Thus, in contrast to storage at
t
050
100150200250300350
no e
xcipi
ent
sucr
ose
treha
lose
inulin
1.8
kDa
inulin
4 kD
a
dextr
an 1
.5 kD
a
dextr
an 5
kDa
par
ticl
e si
ze (
%)
050
100150200250300350
no e
xcipi
ent
sucr
ose
treha
lose
inulin
1.8
kDa
inulin
4 kD
a
dextr
an 1
.5 kD
a
dextr
an 5
kDa
dextr
an 4
0 kD
a
par
ticl
e si
ze (
%)
(a)
(b)de
xtran
40
kDa
Fig. 7. Particle size, as percentage of the value before freeze drying
of nonPEGylated (a) and PEGylated (b) lipoplexes immediately
after freeze drying (n) and after freeze drying and subsequen
storage at 37 8C for 6 days ( ), 1 month ( ), and 3 months ( )
Severely aggregated lipoplexes are indicated by bars that pass the
upper axis.
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479 475
�20 8C, also sucrose, trehalose, and dextran 1.5 kDa
behaved as excellent cryoprotectants under these
conditions. Clearly, this is due to the storage temper-
ature of �85 8C which is well below the Tgs’ of the
sugar solutions. Also noteworthy is the fact that
storage at �20 8C induced a particle size increase of
25–50% in the best cases while upon storage at �85
8C the particle size did not increase at all (except for
dispersions in dextran 5 kDa solutions where for
unknown reasons an increase of about 50% was
measured). The high stability of the dispersions
cannot only be explained by the fact that the storage
temperature was far below the Tgs’ of the sugar
solutions but also by the fact that the cooling rate
preceding storage was much higher (see Material and
methods). When slowly cooled to �20 8C, there is
apparently sufficient time available for moderate
diffusion and consequently limited aggregation during
freeze concentration, which is clearly not the case
when rapidly cooled to �85 8C.PEGylated lipoplexes dispersed in pure buffer
stored at �85 8C fully aggregated within 6 days,
similar to what has been found upon storage at �20
8C (see Fig. 6b). As expected, based on the results
found for nonPEGylated lipoplexes, the particle size
of PEGylated lipoplexes dispersed in sucrose, treha-
lose, and both inulins was fully maintained upon
storage at �85 8C up to 3 months. The same result
was also found for PEGylated lipoplexes dispersed in
dextran 1.5 kDa. However, rapid aggregation occurred
with dextrans of higher molecular weights. The results
are in line with those found at a storage temperature of
�20 8C (see Fig. 5b). As hypothesized above, the
failure of dextran as a cryoprotectant of PEGylated
lipoplexes is due to the incompatibility of dextran
with PEG. This incompatibility increases with the
molecular weight of dextran. Indeed, the stabilizing
capacity of dextran 1.5 kDa at �20 8C was not as poor
as that of the other, larger dextrans. Moreover,
stabilization by dextran 1.5 kDa at �85 8C can even
be considered as excellent. Apparently, a not too
strong incompatibility with PEG in combination with
a fast cooling rate and a low storage temperature
prevents extensive diffusion of dextran 1.5 kDa away
from the PEG shell around the particles. As a result
aggregation is prevented. Contrary to 1.5 kDa dextran,
the incompatibility of higher molecular weight dex-
trans with PEG is apparent such that the driving force
for diffusion of dextran from the PEG shell is very
large and can therefore proceed very fast. As a result
with these large dextrans aggregation is also induced
when the solutions are rapidly cooled to �85 8C.
3.3.3. Effects of freeze drying and subsequent storage
at 37 8C on particle size of lipoplexes
The effect of the sugars on the aggregation
behavior of lipoplexes during freeze drying and
subsequent storage at 37 8C was also evaluated. After
freeze drying in the presence of each of the sugars the
samples appeared as porous cakes and remained so
upon storage at 37 8C. As no collapse was observed, itcan be concluded that the samples were kept well
below their Tg’ and Tg during freeze drying and
storage, respectively. The results of particle size
measurements are summarized in Fig. 7a and b.
NonPEGylated lipoplexes without protectant showed
full aggregation immediately after freeze drying (see
Fig. 7a). Sucrose, trehalose, and both inulins were
,
t
.
0
50
100
150
sucr
ose
treha
lose
inulin
1.8
kDa
inulin
4 kD
a
dextr
an 1
.5 kD
a
dextr
an 5
kDa
dextr
an 4
0 kD
a
zeta
po
ten
tial
(%
)
0
50
100
150
sucr
ose
treha
lose
inulin
1.8
kDa
inulin
4 kD
a
dextr
an 1
.5 kD
a
dextr
an 5
kDa
dextr
an 4
0 kD
a
zeta
po
ten
tial
(%
)
(a)
(b)
Fig. 8. Zeta potential, as percentage of the value before freeze
drying, of nonPEGylated (a) and PEGylated (b) lipoplexes
immediately after freeze drying (n) and after freeze drying and
subsequent storage at 37 8C for 6 days ( ), 1 month ( ), and 3
months ( ). The zeta potentials of severely aggregated lipoplexes
(see Fig. 7) were not measured.
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479476
able to prevent severe aggregation as the size of the
nonPEGylated lipoplexes only increased up to 125%
of their original size. It can be concluded that the
small but significant increase in particle size occurred
during dehydration and not during freezing because
during storage at �85 8C no such increase was
measured (see above). Furthermore, it was found that
these sugars also acted as excellent stabilizers in the
dry state as no further particle size increase was
observed upon storage at 37 8C up to 3 months. Also
the three dextrans were able to prevent aggregation of
the nonPEGylated lipoplexes during freeze drying.
However, upon storage at 37 8C, the results were
somewhat scattered as in some cases (dextran 1.5
kDa) aggregation occurred while in other cases
particle size was more or less maintained. Similar to
the results of the subzero temperature storage experi-
ments (see Figs. 5a and 6a), dextran 40 kDa appeared
to be a remarkable efficient stabilizer during freeze
drying and storage of nonPEGylated lipoplexes,
despite its bulky nature.
The PEGylated lipoplexes behaved similarly except
that dextran 1.5 kDa induced a twofold increase in
particle size during freeze drying which was main-
tained upon storage. However, similarly as observed
for PEGylated lipoplexes (see Figs. 5b and 6b), in
dextran 5 and 40 kDa the PEGylated lipoplexes fully
aggregated immediately after freeze drying.
Both inulins and in some cases dextrans seem thus
as effective as sucrose and trehalose to prevent
lipoplex aggregation during freeze drying and storage.
However, despite the observed equivalence in stabi-
lizing capacities, oligosaccharides are recommended
over disaccharides as lyoprotectants for lipoplex
dispersions especially when exposed to humidified
air. The freeze thaw experiments clearly indicate that
storage below the glass transition temperature (in this
case the Tg’) is essential for maintenance of particle
size. Extrapolating these results to freeze dried
samples it can be hypothesized that upon storage
above the Tg aggregation will also occur. In the
present study, the samples were stored well below the
Tg. However, when exposed to humidified air sugar
glasses will absorb water. The Tg will strongly
decrease upon water absorption and may drop to
below storage temperature. As a result aggregation is
likely to occur. In a previous study, the physical
stability of amorphous disaccharides and inulins was
compared upon exposure to various relative humid-
ities [23,46,47]. It was found that the hygroscopicity
of all these sugars was more or less the same. Because
the Tgs of the dry inulins were much higher than those
of the disaccharides, inulins could be exposed to much
higher relative humidities before the Tg was passed at
a fixed temperature. Similar results can be envisaged
with other oligosaccharides, e.g. dextrans.
3.3.4. Effects on zeta potential of lipoplexes
The zeta potential of all samples stored at �20 or
�85 8C for 3 months, which were not fully aggregated
were somewhat scattered and were 75–125% of the
original values (data not shown). However, because
there was no clear trend and given the accuracy of the
apparatus, changes induced by storage at subzero
temperatures were not considered as being significant.
The zeta potential of all samples, which were not
fully aggregated, was also not significantly affected by
freeze drying (see Fig. 8a and b). However, upon
storage the zeta potential gradually decreased with all
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479 477
the tested lyoprotectants, except trehalose. Because (in
most cases) the particle size remained the same, it can
be suggested that a chemical change occurred at the
surface of the particles. The lipoplexes used in this
study contain the lipid DOPE. At pH 7.4, DOPE is a
Zwitter ion containing a negatively charged phosphate
group and a positively charged primary amine group. It
is well known that amine groups of proteins can react
with reducing groups of sugars to form a Schiff’s base.
Therefore, it can be expected that the amine group of
DOPE will also react with reducing groups of sugars.
This reaction would neutralize the positive charge of
the amine group of DOPE thereby reducing the
positive zeta potential of the particles. Dextrans consist
of a linear a-D-(1Y6) linked glucose oligomer bearing
a-D-(1Y3) linked glucose side chains and contain
therefore reducing end groups. Thus, dextrans allow
the formation of a Schiff’s base. This reaction may be
avoided by chemical modification of the reducing end
groups. Inulins consist of a linear h-D-(2Y1) linked
fructose oligomer ending with a a-D-(1Y2) glucopyr-
anose ring and should therefore contain no reducing
groups. However, commercially available inulins often
also contain reducing sugars like monosaccharides and
inulin species of which the glucose end group is
cleaved [23]. From Fig. 8a and b it can be observed
that the decrease in zeta potential proceeded more
rapidly with the inulin 1.8 kDa containing samples
than with the inulin 4 kDa containing samples. This
can be expected since inulin 1.8 kDa contains more
reducing groups than inulin 4 kDa (data not shown).
These contaminations may be avoided by improved
production and purification methods. Also sucrose is a
non-reducing sugar. However, prolonged storage at
elevated temperatures may induce hydrolysis of the
linkage between the glucose and fructose unit yielding
reducing groups [48]. Indeed, a decrease in zeta
potential is only observed after storage for more than
1 month. Trehalose is also a non-reducing sugar which
is composed of two glucose units. However, it is well
known that trehalose strongly resists hydrolysis [48].
As a consequence, no decrease in zeta potential occurs.
4. Conclusions
The results of this study clearly illustrate that the
oligosaccharides inulin 1.8 and 4 kDa and dextran 1.5,
5, and 40 kDa exhibit better stabilizing properties than
the disaccharides sucrose and trehalose to prevent
aggregation of nonPEGylated lipoplexes during sub-
zero temperature storage of frozen dispersions. It
appeared that the relative high Tgs’ of the oligosac-
charides is the reason for their improved stabilizing
capacity. As a result, during storage at �20 8C particle
size was more or less maintained with the oligosac-
charides (Tg’ around or above �20 8C) while rapid
and severe aggregation occurred in disaccharides
containing solutions (Tg’ below �20 8C). During
freeze drying and storage of the dried powders at 37
8C, both oligosaccharides and disaccharides were able
to preserve particle size of nonPEGylated lipoplexes.
Clearly, particle size was optimally maintained
because in all cases the sample temperature was kept
well below the Tg’ and Tg during freeze drying and
storage, respectively. It is suggested that for storage
purposes, especially upon exposure to humidified air,
oligosaccharides are preferred over disaccharides
because of their higher Tg.
Similar results were found for PEGylated lip-
oplexes with two major differences. First, when stored
above the Tg’, aggregation of the PEGylated lip-
oplexes proceeded at a lower rate than nonPEGylated
lipoplexes, illustrating the steric repulsion effect of
PEG. Second, while inulins showed an adequate
stabilization, dextrans failed to prevent aggregation
of the PEGylated lipoplexes in most cases. This is
most likely caused by the fact that inulins and PEG
are compatible while dextrans and PEG are not.
The zeta potential of all samples remained the same
upon subzero temperature storage. However, the zeta
potential substantially decreased upon storage in the
dry state at 37 8C in all cases except for the trehalose
containing samples where no significant change was
measured. The decrease in zeta potential was most
likely due to the formation of a Schiff’s base.
Concerning the oligosaccharides, this process may
be avoided by improved production and purification
methods of the inulins and by chemical modification
of the end groups of dextran.
In conclusion, oligosaccharides can prevent lip-
oplexes aggregation during subzero temperature stor-
age of frozen dispersions and freeze drying followed
by storage of the dried powder. However, when
PEGylated lipoplexes are considered, the oligosac-
charide should be compatible with PEG. Furthermore,
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479478
the oligosaccharide should contain no reducing
groups to prevent change of the zeta potential.
Maintenance of particle size and zeta potential is not
a guarantee but certainly a prerequisite for mainte-
nance of biological activity. Therefore, future experi-
ments should reveal in detail the effects of
oligosaccharides on the transfection efficiency.
Acknowledgements
The authors wish to thank Ms. Hanne Claerhout,
Ms. Lies Peters, and Ms. Eveline Pringels of the
Department of Pharmaceutics of Ghent University for
their technical assistance.
References
[1] M. Ravi Kumar, G. Hellermann, R.F. Lockey, S.S. Mohapatra,
Nanoparticle-mediated gene delivery: state of the art, Expert
Opin. Biol. Ther. 4 (2004) 1213–1224.
[2] N. McCarthy, Gene therapy-means to an end, Nat. Rev.,
Cancer 4 (2004) 659.
[3] D. Williams, C. Baum, Gene therapy needs both trails and new
strategies, Nature 429 (2004) 129.
[4] P.L. Felgner, T.R. Gadek, M. Holm, R. Roman, H.W. Chan,
M. Wenz, J.P. Northrop, G.M. Ringold, M. Danielsen,
Lipofection: a highly efficient, lipid-mediated DNA-trans-
fection procedure, Proc. Natl. Acad. Sci. U. S. A. 84 (1987)
7413–7417.
[5] A.G. Baranovskii, V.N. Buneva, G.A. Nevinsky, Human
deoxyribonucleases, Biochemistry (Mosc.) 69 (2004)
587–601.
[6] J. Glasspool-Malone, P.R. Steenland, R.J. McDonald, R.A.
Sanchez, T.L. Watts, J. Zabner, R.W. Malone, DNA trans-
fection of macaque and murine respiratory tissue is greatly
enhanced by use of a nuclease inhibitor, J. Gene Med. 4 (2002)
323–332.
[7] F.D. Ledley, Pharmaceutical approach to somatic gene therapy,
Pharm. Res. 13 (1996) 1595–1614.
[8] T. Segura, L.D. Shea, Material for non-viral gene delivery,
Annu. Rev. Mater. Res. 31 (2001) 25–46.
[9] N.N. Sanders, E. Van Rompaey, S.C. De Smedt, J. Demeester,
Structural alterations of gene complexes by cystic fibrosis
sputum, Am. J. Respir. Crit. Care Med. 164 (2001) 486–493.
[10] H.Y. Li, H. Neill, R. Innocent, P. Seville, I. Williamson, J.C.
Birchall, Enhanced dispersibility and deposition of spray-dried
powders for pulmonary gene therapy, J. Drug Target. 11
(2003) 425–432.
[11] P.C. Seville, I.W. Kellaway, J.C. Birchall, Preparation of dry
powder dispersions for non-viral gene delivery by freeze-
drying and spray-drying, J. Gene Med. 4 (2002) 428–437.
[12] M. Tservistas, M.S. Levy, M.Y. Lo-Yim, R.D. O’Kennedy, P.
York, G.O. Humphrey, M. Hoare, The formation of plasmid
DNA loaded pharmaceutical powders using supercritical fluid
technology, Biotechnol. Bioeng. 72 (2001) 12–18.
[13] W. Wang, Lyophilization and development of solid protein
pharmaceuticals, Int. J. Pharm. 203 (2000) 1–60.
[14] D.J. van Drooge, W.L.J. Hinrichs, K.A.M. Wegman, M.R.
Visser, A.C. Eissens, H.W. Frijlink, Solid dispersions based on
inulin for the stabilisation and formulation of Delta 9-
tetrahydrocannabinol, Eur. J. Pharm. Sci. 21 (2004) 511–518.
[15] M.A. Croyle, X. Cheng, J.M. Wilson, Development of
formulations that enhance physical stability of viral vectors
for gene therapy, Gene Ther. 8 (2001) 1281–1290.
[16] J. Crowe, L.M. Crowe, J.F. Carpenter, C.A. Wistrom,
Stabilization of dry phospholipid bilayers and proteins by
sugars, Biochem. J. 242 (1987) 1–10.
[17] T.J. Anchordoquy, G.S. Koe, Physical stability of nonviral
plasmid-based therapeutics, J. Pharm. Sci. 89 (2000)
289–296.
[18] T.J. Anchordoquy, S.D. Allison, M.C. Molina, L.G. Girouard,
T.K. Carson, Physical stabilization of DNA-based therapeu-
tics, Drug Discov. Today 6 (2001) 463–470.
[19] S.D. Allison, M.D.C. Molina, T.J. Anchordoguy, Stabilization
of lipid/DNA complexes during the freezing step of the
lyophilization process: the particle isolation hypothesis, Bio-
chim. Biophys. Acta 1468 (2000) 127–138.
[20] M.C. Molina, T.K. Armstrong, Y. Zhang, M.M. Patel, Y.K.
Lentz, T.J. Anchordoguy, The stability of lyophilized lipid/
DNA complexes during prolonged storage, J. Pharm. Sci. 93
(2004) 2259–2273.
[21] S.D. Allison, T.J. Anchordoquy, Mechanisms of protection of
cationic lipid–DNA complexes during lyophilization, J. Pharm.
Sci. 89 (2000) 682–691.
[22] T.J. Anchordoquy, J.F. Carpenter, D.J. Kroll, Maintenance of
transfection rates and physical characterization of lipid/DNA
complexes after freeze drying, Arch. Biochem. Biophys. 348
(1997) 199–206.
[23] W.L.J. Hinrichs, M.G. Prinsen, H.W. Frijlink, Inulin glasses
for the stabilization of therapeutic proteins, Int. J. Pharm. 215
(2001) 163–174.
[24] M.C.. Molina, S.D. Allison, T.J. Anchordoquy, Maintenance
of nonviral vector particle size during the freezing step of the
lyophilization process is insufficient for preservation of
activity: insight from other structural indicators, J. Pharm.
Sci. 90 (2001) 1445–1455.
[25] M.C. Heller, J.F. Carpenter, T.W. Randolph, Conformational
stability of lyophilized PEGylated proteins in a phase-
separated system, J. Pharm. Sci. 88 (1999) 58–64.
[26] K. Izutsu, S. Yoshioka, S. Kojima, T.W. Randolph, J.F.
Carpenter, Effects of sugars and polymers on crystallization
of poly(ethylene glycol) in frozen solutions: phase separation
between incompatible polymers, Pharm. Res. 13 (1996)
1393–1400.
[27] L. Slade, H. Levine, Beyond water activity: recent advances
based on an alternative approach to the assessment of food
quality and safety, Crit. Rev. Food Sci. Nutr. 30 (1991)
115–360.
W.L.J. Hinrichs et al. / Journal of Controlled Release 103 (2005) 465–479 479
[28] H. Levine, L. Slade, Water as a plasticizer: physico-chemical
aspects of low-moisture polymeric systems, Water Sci. Rev. 3
(1988) 79–185.
[29] L.-M. Her, S.L. Nail, Measurement of glass transition
temperatures of freeze-concentrated solutes by differential
scanning calorimetry, Pharm. Res. 11 (1994) 54–59.
[30] L.A. Schaller-Povolny, D.E. Smith, T.P. Labuza, Effect of
water content and molecular weight on the moisture isotherms
and glass transition properties of inulin, Int. J. Food Prop. 3
(2000) 173–192.
[31] G.T. Fox, P.J. Flory, Second-order transitions temperatures and
related properties of polystyrene: I. Influence of molecular
weight, J. Appl. Phys. 21 (1950) 581–591.
[32] J.H. Eriksson, W.L. Hinrichs, G.J. de Jong, G.W. Somsen,
H.W. Frijlink, Investigations into the stabilization of drugs by
sugar glasses: III. The influence of various high-pH buffers,
Pharm. Res. 20 (2003) 1437–1443.
[33] S. Rossi, M.P. Buera, S. Moreno, J. Chirife, Stabilization of
the restriction enzyme EcoRI dried with trehalose and other
selected glass-forming solutes, Biotechnol. Prog. 13 (1997)
609–616.
[34] M. Scandola, G. Ceccorulli, M. Pizzoli, Molecular motions of
polysaccharides in the solid state: dextran, pullulan and
amylose, Int. J. Biol. Macromol. 13 (1991) 254–260.
[35] J.H. van Steenis, E.M. van Maarseveen, F.J. Verbaan, R.
Verrijk, D.J.A. Crommelin, G. Storm, W.E. Hennink, Prepa-
ration and characterization of folate-targeted pEG-coated
pDMAEMA-based polyplexes, J. Control Release 87 (2003)
167–176.
[36] J.O. Radler, I. Koltover, T. Salditt, C.R. Safinya, Structure of
DNA-cationic liposome complexes: DNA intercalation in
multilamellar membranes in distinct interhelical packing
regimes, Science 275 (1997) 810–814.
[37] O. Zelphati, F.C. Szoka Jr., Mechanism of oligonucleotide
release from cationic liposomes, Proc. Natl. Acad. Sci. U. S.
A. 93 (1996) 11493–11498.
[38] P.A. Albertsson, Partition of Cell Particles and Macromole-
cules, Wiley-Interscience, New York, 1986.
[39] R.J. Stenekes, O. Franssen, E.M. van Bommel, D.J. Cromme-
lin, W.E. Hennink, The preparation of dextran microspheres in
an all-aqueous system: effect of the formulation parameters on
particle characteristics, Pharm. Res. 15 (1998) 557–561.
[40] M.C. Heller, J.F. Carpenter, T.W. Randolph, Application of a
thermodynamic model to the prediction of phase separations in
freeze-concentrated formulations for protein lyophilization,
Arch. Biochem. Biophys. 363 (1999) 191–201.
[41] M.C. Heller, J.F. Carpenter, T.W. Randolph, Manipulation
of lyophilization-induced phase separation: implications for
pharmaceutical proteins, Biotechnol. Prog. 13 (1997)
590–596.
[42] M.C. Heller, J.F. Carpenter, T.W. Randolph, Effects of phase
separating systems on lyophilized hemoglobin, J. Pharm. Sci.
85 (1996) 1358–1362.
[43] K. Amin, R.M. Dannenfelser, J. Zielinski, B. Wang, Lyophi-
lization of polyethylene glycol mixtures, J. Pharm. Sci. 93
(2004) 2244–2249.
[44] I.J. Vereyken, J.A. Van Kuik, T.H. Evers, P.J. Rijken, B. De
Kruijff, Structural requirements of the fructan–lipid interac-
tion, Biophys. J. 84 (2003) 3147–3154.
[45] T.K. Armstrong, L.G. Girouard, T.J. Anchordoquy, Effects of
PEGylation on the preservation of cationic lipid/DNA com-
plexes during freeze-thawing and lyophilization, J. Pharm. Sci.
91 (2002) 2549–2558.
[46] D.J. van Drooge, W.L.J. Hinrichs, H.W. Frijlink, Incorporation
of lipophilic drugs in sugar glasses by lyophilization using a
mixture of water and tertiary butyl alcohol as solvent, J. Pharm.
Sci. 93 (2004) 713–725.
[47] H.J. Eriksson, W.L. Hinrichs, B. van Veen, G.W. Somsen, G.J.
de Jong, H.W. Frijlink, Investigations into the stabilisation of
drugs by sugar glasses: I. Tablets prepared from stabilised
alkaline phosphatase, Int. J. Pharm. 249 (2002) 59–70.
[48] C.A.L.S. Colaco, C.J.S. Smith, S. Sen, D.H. Roser, Y.
Newman, S. Ring, B.J. Roser, Chemistry of protein stabiliza-
tion by trehalose, ACS Symp. Ser. 567 (1994) 222–240.