ORIGINAL ARTICLE
Effects of Cross-linker Variation on
Swelling Behavior of Hydrogels
Farheen Rahman1, M. Z. A. Rafiquee1, Elham S. Aazam2, S. M. Shakeel Iqubal3,
Aejaz A. Khan3, Tasneem Mohammed3, Muazzam Sheriff Maqbul4,
Areej Dawoud3, Kayamkani Abedulla Khan5, Abdul Rahman Ikbal3
1
Department of Applied Chemistry, Z.H. College of Engineering and Technology, Aligarh Muslim University,
Aligarh, Uttar Pradesh, India, 2Department of Chemistry, King Abdul Aziz University, Jeddah, Kingdom of Saudi
Arabia, 3Department of General Science, Ibn Sina National College of Medical Sciences, Jeddah 21418,
Kingdom of Saudi Arabia, 4Faculty of Microbiology and Immunology, Ibn Sina National College of Medical
Sciences, Al Mahjar Street: 31906, Jeddah 21418, Kingdom of Saudi Arabia, 5Department of Clinical Pharmacy
and Pharmacology, Ibn Sina National College for Medical Studies, Jeddah, Kingdom of Saudi Arabia
Abstract
Introduction: The main objective of this study is to find the effects of cross-linker variation on swelling behavior
of hydrogels at different temperatures, that is, 30 min–120 min. Hydrogels are three-dimensional cross-linked
structural arrangement of the polymeric materials with the ability to absorb huge amounts of water while maintaining
their dimensional stability. Materials and Methods: A solution of 20% glutaraldehyde (GA) was prepared in 100
ml standard flask by dissolving 20.0 g GA in a standard flask (of capacity 100 ml) and make up the volume up to
the mark using demineralized water (DMW). The gelatin-polyethylene glycol (PEG) composite hydrogels were
prepared by simultaneous method, in which all the constituent component networks are polymerized concurrently.
Different combinations of gelatin-PEG composite hydrogels were prepared with methylene blue (MB) dye in it.
Wd - Ws
Swelling was studied with the help of the following equation:
=
Is
×100 Results and Discussion: The
Wd
observation showed that the decrease in the absorbance of MB release through the sample membrane may be due
to the contraction of the microvoids formed between the polymeric chains. Conclusion: Based on our results
which conclude that with increasing crosslinking agent from 5 ml to 15 ml, swelling ratio of the prepared sample
decreased from 473.83 to 428.97 in DMW due to the decrease in the pore diameter of the sample. As a result, more
and more solvent diffuses into the matrix and produce gel with increased swelling ratio.
Key words: Cross-linkers, dye, gelatin, glutaraldehyde, hydrogels, polyethylene glycol, spectrophotometer,
swelling
H
INTRODUCTION
ydrogels are three-dimensional crosslinked structural arrangement of the
polymeric materials with the ability to
absorb huge amounts of water while maintaining
their dimensional stability.[1] Hydrogels on the
basis of origins can be classified as natural
or synthetic.[2] Hydrogel-forming natural
polymers are proteins (collagen and gelatin)
and polysaccharides (alginate and agarose).
These hydrogels have low toxicity and good
biocompatibility.[3] The synthetic polymers
that form hydrogels are usually obtained
through chemical polymerization methods
by crosslinking the materials of desirable
properties.[4] These hydrogels may have lower
interfacial tension, soft and tissue like physical characters,
greater permeability to undersized molecules, and release
of entrapped molecules in a controlled manner.[4] These
properties have made hydrogels a focus of exploration in
different biomedical fields, for example, include wound
dressings, super absorbents, drug delivery systems, and
tissue engineering.[1] Many of the hydrogels are responsive
to fluctuations in physical and chemical stimuli such as
Address for correspondence:
Dr. S. M. Shakeel Iqubal, Department of General
Science, Ibn Sina National College for Medical Studies,
Jeddah, Saudi Arabia. E-mail: shakeeliqubal@gmail.com
Received: 13-05-2020
Revised: 07-06-2020
Accepted: 13-06-2020
Asian Journal of Pharmaceutics • Jul-Sep 2020 • 14 (3) | 351
Rahman, et al.: Crosslinker variation of hydrogels
temperature, electric fields, solvent composition, light,
pressure, sound and magnetic fields, pH, ions, and specific
molecular recognition events.[5] Such hydrogels are
called “smart hydrogels” and find applications in making
actuators and valves, in the immobilization of enzymes
and cells, in sensors, and in concentrating dilute solutions
in bioseparation.[1] The properties of hydrogels such as
swelling, mechanical, and biocompatible properties are
important for its applications in engineering or other areas
of biomedical fields.[2] These properties largely depend
on the constituent materials and methods of preparations.
Cross-linked networks of one type of hydrophilic monomer
unit, for example, polyethylene glycol (PEG), polyvinyl
alcohol, polyvinylpyrrolidone, polyacrylic acid, etc., were
used to prepare homopolymer hydrogels. Two comonomer
units are cross linked to produce the copolymer hydrogels.
In this process, at least one of the monomer must be
hydrophilic to make them swellable, for example, triblock
poly(ethylene glycol)-poly(ε-caprolactone)-poly(ethylene
glycol), copolymer of glycerol, and polyethylene oxide
of different molecular weights.[6] The interpenetrating
polymeric hydrogels are produced by the penetration of one
cross-linked network into another linear polymer without any
other chemical bonds between them. Due to the absence of
restricting interpenetrating elastic network, interpenetrating
networks (IPNs) can further adequately secure rapid kinetic
response rates to temperature or pH, for example, entrapment
of linear cationic polyallyl ammonium chloride in acrylamide/
acrylic acid copolymer hydrogel.[4,5,7] IPNs are conventionally
described as intimate mixture of two polymers, at least one
of which is cross-linked or synthesized in the instantaneous
presence of the other, for example, PEG diacrylate hydrogels
modified with β-chitosan.[1,8] This process accomplished by
immersing a pre-polymerized hydrogel into a solution of
polymerization initiator and monomers. IPN method can
overcome thermodynamic incompatibility. This happens
due to the constant interlocking of network segments and
restricted phase separation can be acquired. The stability of
the bulk and surface morphology is ensured by the interlocked
structure of the cross-linked IPN components.[2] The IPNs
are relatively dense hydrogel with stiffer and tougher
mechanical properties, controllable physical properties,
and more efficient drug loading compared to conventional
hydrogels. IPN pore sizes and surface chemistries can also
be controlled to tune the drug release kinetics, interaction
between the hydrogel and the surrounding tissues along with
its mechanical properties.[9,10]
Types of hydrogels
Stimuli responsive hydrogels, pH responsive hydrogels,
temperature responsive hydrogels, thermoreversible
hydrogels, glucose responsive hydrogels, antigen-responsive
hydrogels, light-sensitive system ion sensitive system, and
magnetically responsive system.[2,6,7]
MATERIALS AND METHODS
Methylene blue (MB) (S. D Fine, India), PEG (SigmaAldrich Chemicals [USA]), glutaraldehyde (GA) (S. D Fine,
India), hydrochloric acid (HCl) (S. D Fine, India), and gelatin
(GE) (Fluka [Buchs, Switzerland]) were used. All reagents
and chemicals used were of analytical grades.
Preparation of stock solutions
Preparation 1000 ppm of MB solution
The stock solution of MB of 1000 ppm was prepared by
dissolving 0.1 g of MB dye in a 100 ml standard volumetric
flask. The stock solution of the dye was kept in dark to protect
it from any photochemical reactions.[11]
Preparation of 0.1 M HCl solution
The stock solution of 0.1 M HCl was prepared by dissolving
0.90 ml HCl in demineralized water (DMW) in a 100 ml
standard flask.
Preparation of 20% GA solution
A solution of 20% GA was prepared in 100 ml standard flask
by dissolving 20.0 g GA in a standard flask (of capacity
100 ml) and make up the volume up to the mark using DMW.
Preparation of gelatin-PEG composite hydrogels
The gelatin-PEG composite hydrogels were prepared
by simultaneous method in which all the constituent
component networks are polymerized concurrently. Different
combinations of gelatin-PEG composite hydrogels were
prepared with MB dye in it. To make them homogeneous,
components were thoroughly mixed by stirring the solution
during preparation.[8,11] The composition of the prepared
samples is given in Table 1.
Properties of hydrogels
Swelling study
The most important characteristic properties of the hydrogels
that are needed to be evaluated before their applications are
swelling behavior: One of the most important properties
of hydrogels is its ability to absorb liquids (swelling
thermodynamics) and the rate at which the hydrogels absorb
the liquid (swelling kinetics).[6]
The maximum hydration capacity of the gelatin and PEG
hydrogel was determined by weighing the dried sample
(Wd) and then weighing the sample again after immersion
in DMW at room temperature for 30 min.[6] The water
absorption of the sample was calculated using the following
equation:
Asian Journal of Pharmaceutics • Jul-Sep 2020 • 14 (3) | 352
Rahman, et al.: Crosslinker variation of hydrogels
Table 1: Weights of the chemicals taken in different formulations of hydrogels
Components
Samples prepared
SP1
SP2
SP3
SP4
SP5
SP6
SP7
Gelatin (g)
2.0
2.0
2.0
2.0
2.0
3.0
4.0
Polyethylene glycol (g)
0.5
0.5
0.5
0.5
1.5
0.5
2.5
Methylene blue (1000 ppm) (ml)
10.0
10.0
5.0
5.0
5.0
5.0
5.0
Glutaraldehyde (ml)
10.0
20.0
10.0
5.0
10
10
15.0
=
Is
Wd - Ws
×100
Wd
Where, Is is the percentage swelling index.
RESULTS AND DISCUSSION
Effects of cross-linker variation on dye release
Table 2: Swelling ratio comparison in sample-3, 4,
and 7 in demineralized water (GA variation)
Time taken
(minutes)
Sample-4
(5 ml GA)
Sample-3
(10 ml GA)
Sample-7
(15 ml GA)
30
356.07477
241.1215
167.28972
60
411.21495
372.8972
295.3271
90
450.46729
421.49533
390.65421
120
473.83178
452.33645
428.97196
GA: Glutaraldehyde
Tables 2 and 3 determine the membrane dye releasing property
due to the variations of cross-linker (5 ml, 10 ml, and 15 ml)
which shows the release behavior of MB from the membrane
in the hydrogel compositions S.P-3, 4, and 7 in DMW and 0.1
M HCl, respectively.[3,12,13] The observation showed that the
decrease in the absorbance of MB release through the sample
membrane may be due to the contraction of the microvoids
formed between the polymeric chain. Obtained experimental
results illustrate that with increasing crosslinking agent from
5 ml to 15 ml, absorbance of the prepared sample decreased
from 0.426 to 0.422 in DMW and 0.474 to 0.419 in 0.1 M
HCl due to decrease in the pore diameter of the sample.[4,9,10]
Effects of cross-linker variation on swelling
behavior
Table 3: Swelling ratio comparison in sample-3, 6,
and 7 in demineralized water (Ge variation)
Time taken
(minutes)
Sample-3
(2 g Ge)
Sample-6 (3
g Ge)
Sample-7
(4 g Ge)
30
295.33
392.52
513.08
60
378.50
500.00
593.46
90
477.57
658.88
718.69
120
543.93
749.53
796.26
Table 4: Swelling ratio comparison in sample-3, 6,
and 7 in 0.1 M HCl (Ge variation)
Time taken
(minutes)
Sample-3 (2
g Ge)
Sample-6
(3 g Ge)
Sample-7
(4 g Ge)
30
294.39
379.44
420.56
60
379.30
426.17
483.18
90
476.96
514.02
552.34
120
544.33
596.26
616.82
Table 2 determines the membrane swelling property due
to the variation of cross-linker (5 ml, 10 ml, and 15 ml) in
the hydrogel compositions S.P-3, 4, and 7 in DMW. The
observation showed that the decrease in the swelling ratio
of the sample membrane may be due to the contraction of
the microvoids formed between the polymeric chains.[4,9,10]
Obtained experimental result illustrates that with increasing
crosslinking agent from 5 ml to 15 ml, swelling ratio of the
prepared sample decreased from 473.83 to 428.97 [Table 2] in
DMW due to the decrease in the pore diameter of the sample.
ratio of the prepared sample also increased. This is due to
the hydrophilic nature of gelatin that the interaction between
the solvent and gelatin increased which result into swollen
hydrogel.[12]
Effects of gelatin on swelling ratio
Effects of PEG on swelling behavior
Tables 3 and 4 determine the swelling behavior of
compositions containing varying amount of gelatin (2 g, 3 g,
and 4 g) at fixed GA and PEG in the hydrogel compositions
S.P-3, 6, and 7 in DMW and 0.1 M HCl, respectively.
According to the experimental result, we conclude that with
increasing gelatin composition from 2 g to 4 g, swelling
Tables 5 and 6 determine the swelling behavior of the
compositions containing varying amount of PEG (0.5 g,
1.5 g, and 2.5 g) with fixed amount of GA and gelatin in
hydrogel compositions S.P-3, 5, and 7 in DMW and 0.1
M HCl, respectively.[5,8] The observation showed that with
increasing PEG compositions from 0.5 g to 2.5 g, swelling
Asian Journal of Pharmaceutics • Jul-Sep 2020 • 14 (3) | 353
Rahman, et al.: Crosslinker variation of hydrogels
Table 5: Swelling ratio comparison in sample-3, 5,
and 7 in demineralized water (PEG variation)
Time taken
(minutes)
Sample-3
(0.5 g PEG)
Sample-5
(1.5 g PEG)
Sample-7
(2.5 g PEG)
30
294.91
614.02
783.18
60
376.98
912.15
1033.64
90
476.86
1061.68
1228.04
120
542.99
1116.82
1331.78
PEG: Polyethylene glycol
ACKNOWLEDGMENT
The authors are thankful to Chairman of the Department
of Applied Chemistry, Z.H. Engineering College, Aligarh
Muslim University, Aligarh, 202002, and administration of
Ibn Sina National College, Jeddah, K.S.A., for giving us
constant encouragement, support, and blessings. In addition
to this, we are also grateful to Prof. Zaheer Khan, Department
of Chemistry, King Abdul Aziz University, Jeddah, Kingdom
of Saudi Arabia, for their suggestions for this manuscript.
Table 6: Swelling ratio comparison in sample-3, 5,
and 7 in 0.1 M HCl (PEG variation)
Time taken
(minutes)
Sample-3
(0.5 g PEG)
Sample-5
(1.5 g PEG)
Sample-7
(2.5 g PEG)
30
296.18
551.40
687.85
60
377.41
658.88
808.41
90
478.21
661.68
821.50
120
544.13
707.48
943.93
PEG: Polyethylene glycol
ratio of the prepared sample also increased.[12] This may
be due to the hydrophilic nature of PEG that the increased
in the PEG amount suggested its increased interaction
with the nearby solvent which causes swelling of the
microvoids. As a result, more and more solvent diffuses
into the matrix and produce gel with increased swelling
ratio.
CONCLUSION
Based on our results which conclude that with increasing
crosslinking agent from 5 ml to 15 ml, swelling ratio of the
prepared sample decreased from 473.83 to 428.97 in DMW
due to the decrease in the pore diameter of the sample.
Increasing gelatin composition from 2 g to 4 g, swelling
ratio of the prepared sample also increased, due to the
hydrophilic nature of gelatin that the interaction between
the solvent and gelatin increased which result into swollen
hydrogel. Increasing PEG compositions from 0.5 g to 2.5 g,
swelling ratio of the prepared sample also increased, due
to the hydrophilic nature of PEG that the increased in the
PEG amount suggested its increased interaction with the
nearby solvent which causes swelling of the microvoids. As
a result, more and more solvent diffuses into the matrix and
produces gel with increased swelling ratio. Due to their high
biocompatibility and water absorption capacity, they have
been used in dental materials, wound dressing, implants, drug
delivery, injectable polymeric systems, agriculture, sanitary
pads as well as transdermal systems, ophthalmic applications,
hybrid-type organs, etc.
CONFLICTS OF INTEREST
No conflicts of interest.
CONTRIBUTION OF AUTHORS
All authors have made substantial contribution to the work
and approved it for publication.
FUNDING
None.
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Source of Support: Nil. Conflicts of Interest: None declared.
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