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SYNTHESIS, CHARACTERISATION AND IN
VITRO EVALUATION OF DISULPHIDE CROSS-
LINKED POLYMERS AS POTENTIAL
CARRIERS FOR COLON SPECIFIC DRUG
DELIVERY SYSTEM
LAU YONG KHEE
UNIVERSITI SAINS MALAYSIA
2015
SYNTHESIS, CHARACTERISATION AND IN VITRO EVALUATION OF
DISULPHIDE CROSS-LINKED POLYMERS AS POTENTIAL CARRIERS
FOR COLON SPECIFIC DRUG DELIVERY SYSTEM
by
LAU YONG KHEE
Thesis submitted in fulfillment of the
requirements for the Degree
of Master of Science
FEBRUARY 2015
i
To my beloved parents, Lau Leong Bee and Lim Guat Hong,
and my brother, Lau Kian Khee
ii
ACKNOWLEDGEMENTS
I own my most sincere thanks to Dr. Lim Vuanghao, my wonderful and
helpful supervisor for giving me the opportunity to carry out this study. I have been
very fortunate to have Dr. Lim, a great mentor who gave me guidance during this
course of work and provided me with constructive comments and criticism. I am
deeply grateful to Dr. Nurzalina Karim Khan and Dr. Lee Hooi Ling, both my great
co-supervisors who guided me and unrelenting supported me throughout my research.
I would also express my special thanks to my wonderful friends and
colleagues, Siti Aishah, Masturah, Nurul Azieyan, Asila Dinie and Hui Wen for their
continuous support, understanding, encouragement and technical assistance. My
deepest appreciation also goes to the director and staffs of IPPT, USM for all their
support and assistance rendered during the course of my study.
Finally, I extend my deepest thanks to my family and my dearest girlfriend,
Renly who suffered when I should have been at home with them rather than working
on this research.
Lau Yong Khee
February 2015
iii
TABLE OF CONTENTS
Page
ACKNOWLEDGEMENTS ii
TABLE OF CONTENTS iii
LIST OF TABLES xi
LIST OF FIGURES xii
LIST OF SCHEMES xvii
LIST OF ABREVIATIONS xviii
ABSTRAK xx
ABSTRACT xxii
CHAPTER ONE : INTRODUCTION
1.1 Backgroud 1
1.2 Anatomy of the colon 2
1.3 Microflora of the gastrointestinal tract 4
1.4 Colon-specific drug targeting 7
1.5 Strategies for targeting drugs to the colon 8
1.5.1 pH responsive delivery 8
1.5.2 Time responsive delivery 10
1.5.3 Pressure responsive delivery 12
1.5.4 Bacteria responsive delivery 13
1.5.4.1 Azo-containing prodrugs 13
1.5.4.2 Azo polymers 16
1.5.4.3 Glycosidic prodrugs 17
iv
1.5.4.4 Polysaccharides 18
1.5.4.5 Disulphide polymers 21
1.6 Literature review 22
1.7 Aim of the thesis 30
CHAPTER TWO : SYNTHESIS OF TRITHIOL MONOMER
2.1 Introduction 31
2.2 Objective 32
2.3 Materials 32
2.4 Physical characterisation of synthesised compounds 33
2.4.1 Qualitative screening of synthesised compound 33
2.4.2 Spectroscopic analysis 33
2.4.3 Liquid Chromatography-Mass Spectrometry (LC-MS) 33
2.4.4 Elemental analysis and melting point tests 34
2.5 Experimental procedures 34
2.5.1 Synthesis of (triphenylmethyl) thioethylamine (3) 34
2.5.2 Synthesis of N,N',N''-tris[2-(tritylsulfanyl)ethyl]propane-1,2,3-
tricarboxamide (5) (tricarballylic acid based trityl monomer) 35
2.5.3 Deprotection of (5) to yield N,N',N''-tris(2-sulfanylethyl)
propane-1,2,3-tricarboxamide (6) (tricarballylic acid based
trithiol monomer) 36
2.5.4 Attempted synthesis of N,N',N''-tris(2-sulfanylethyl)prop-1-
ene-1,2,3-tricarboxamide (8) (aconitic acid based trityl
monomer) 37
2.6 Results and discussion 40
2.6.1 Elucidation of (triphenylmethyl) thioethylamine (3) 40
2.6.2 Elucidation of N,N',N''-tris[2-(tritylsulfanyl)ethyl]propane-
1,2,3-tricarboxamide (5) 42
v
2.6.3 Elucidation of N,N',N''-tris(2-sulfanylethyl)propane-1,2,3-
tricarboxamide (6) 44
2.6.4 General discussion 46
2.7 Conclusion 50
CHAPTER THREE : SYNTHESIS OF DISULPHIDE CROSS-
LINKED POLYMERS
3.1 Introduction 51
3.2 Objective 51
3.3 Materials and methods 52
3.3.1 Materials 52
3.3.2 Polymerisation 52
3.3.2.1 Oxidation of trithiol monomers 52
3.3.2.2 Detection of thiol with sodium nitroprusside reagent,
Na2Fe(CN)5NO 53
3.3.2.3 Physical characterisation of the synthesised polymers 53
3.3.2.4 Scanning Electron Microscope-Energy Dispersive
X-ray (SEM- EDX) 54
3.3.2.5 Raman spectroscopy 54
3.4 Results 54
3.4.1 Physical characterisations of disulphide cross-linked polymers 54
3.4.1.1 Solubility test for disulphide cross-linked polymers 55
3.4.1.2 Characterisation of disulphide cross-linked polymers 56
3.4.1.3 Raman spectroscopy 63
3.4.1.4 SEM for morphology aspects and EDX micrographs 63
3.4.1.5 Elemental mapping 70
3.5 Discussion 76
vi
3.6 Conclusion 81
CHAPTER FOUR : CHEMICAL REDUCTION STUDIES OF
DISULPHIDE CROSS-LINKED POLYMERS
4.1 Introduction 82
4.2 Objective 82
4.3 Materials and methods 83
4.3.1 Materials 83
4.3.1.1 Reagent for assay of thiols 83
4.3.1.2 Materials for chemical reduction 83
4.3.1.3 Polymer substrates 83
4.3.2 Assay for thiol 84
4.3.2.1 Preparation of Sørensen’s phosphate buffer 84
4.3.2.2 Determination of thiol content using Ellman’s reagent 84
4.3.2.3 Application of Beer-Lambert equation 85
4.4 Chemical reduction 85
4.4.1 Reduction of cystamine dihydrochloride by zinc/acetic acid 85
4.4.2 Reduction of disulphide cross-linked polymers by zinc/acetic 85
acid
4.5 Results 87
4.5.1 Chemical reduction of cystamine dihydrochloride 87
4.5.2 Chemical reduction of disulphide cross-linked polymers 89
4.5.2.1 Chemical reduction of polymer P10 89
4.5.2.2 Chemical reduction of polymer P11 90
4.5.2.3 Chemical reduction of polymer P12 91
4.5.2.4 Chemical reduction of polymer P15 92
vii
4.5.2.5 Chemical reduction of polymer P21 93
4.5.2.6 Chemical reduction of polymer P51 94
4.6 Discussion 96
4.6.1 Chemical reduction of cystamine dihydrochloride 96
4.6.2 Chemical reduction of disulphide cross-linked polymers 96
4.7 Conclusion 98
CHAPTER FIVE : DISSOLUTION STUDIES OF DISULPHIDE
CROSS-LINKED POLYMERS
5.1 Introduction 99
5.2 Objective 100
5.3 Materials 100
5.3.1 Pure culture bacteria 100
5.3.2 Incubation media 101
5.3.3 Other materials 101
5.3.4 Polymer substrates 101
5.4 Experimental procedures 102
5.4.1 Bacteriological techniques 102
5.4.2 Preparation of pre-reduced anaerobically sterile media 102
(PRAS-WCAB)
5.4.3 Preparation of Robertson’s cooked meat media (CMM) 103
5.4.4 Preparation of WCAB Bacteroides fragilis test culture 103
5.4.5 Preparation of bacterial pellets 104
5.4.6 Preparation of Bacteroides fragilis stock cultures 104
5.4.7 Preparation of Sørensen’s phosphate buffer pH 7.4 104
5.4.8 Polymer sample preparation 105
viii
5.4.9 Preparation of simulated gastric fluid 105
5.4.10 Preparation of simulated intestinal fluid 106
5.4.11 Degradation in simulated gastric fluid 106
5.4.12 Degradation in simulated intestinal fluid 107
5.4.13 Incubation of disulphide cross-linked polymers with
Bacteroides fragilis in Sørensen’s phosphate buffer 107
5.4.14 Control incubations 108
5.4.15 Detection thiol concentration using Ellman’s reagent 108
5.5 Results 108
5.5.1 Dissolutions of polymers in simulated gastric condition 109
5.5.1.1 Dissolution of polymer P10 in simulated gastric 109
condition
5.5.1.2 Dissolution of polymer P11 in simulated gastric 110
condition
5.5.1.3 Dissolution of polymer P12 in simulated gastric 111
condition
5.5.1.4 Dissolution of polymer P15 in simulated gastric 112
condition
5.5.1.5 Dissolution of polymer P21 in simulated gastric 113
condition
5.5.1.6 Dissolution of polymer P51 in simulated gastric 114
condition
5.5.1.7 Dissolution of polymer P10 in simulated intestine 115
condition
5.5.1.8 Dissolution of polymer P11 in simulated intestine 116
condition
5.5.1.9 Dissolution of polymer P12 in simulated intestine 117
condition
5.5.1.10 Dissolution of polymer P15 in simulated intestine 118
condition
ix
5.5.1.11 Dissolution of polymer P21 in simulated intestine 119
condition
5.5.1.12 Dissolution of polymer P51 in simulated intestine 120
condition
5.5.1.13 Incubation of polymer P10 in simulated colon 121
condition
5.5.1.14 Incubation of polymer P11 in simulated colon 122
condition
5.5.1.15 Incubation of polymer P12 in simulated colon 123
condition
5.5.1.16 Incubation of polymer P15 in simulated colon 124
condition
5.5.1.17 Incubation of polymer P21 in simulated colon 125
condition
5.5.1.18 Incubation of polymer P51 in simulated colon 126
condition
5.5.1.19 Summary of the thiol concentrations detected from 127
each formulated polymer after dissolution studies
5.5.2 Statistical analysis results 128
5.6 Discussion 132
5.7 Conclusion 135
CHAPTER SIX : GENERAL DISCUSSION 137
CHAPTER SEVEN : FURTHER STUDIES 141
7.1 Employ 2,2’-thiodiethanethiol as alternative dithiol monomer for 141
polymerisation
7.2 Use iodine as the oxidising agent for polymerisation 142
7.3 Coating of gelatine capsule by using disulphide cross-linked 142
polymers
x
REFERENCES 143
APPENDICES
Appendix A 158
Appendix B 158
Appendix C 159
Appendix D 159
Appendix E 160
Appendix F 160
Appendix G 161
Appendix H 161
Appendix I 162
Appendix J 162
Appendix K 163
Appendix L 163
xi
LIST OF TABLES
Table 2.1
Table 2.2
Table 2.3
Table 3.1
CHNS analysis of (3).
CHNS analysis of (5).
CHNS analysis of (6).
Solubility test of the synthesised polymers at
different molar ratios.
41
43
45
55
Table 3.2 Morphology of synthesised disulphide polymers. 56
Table 4.1 Thiol concentration of chemical reduction for six
formulated disulphide polymers.
95
Table 5.1 Dissolution studies of detected thiol concentrations
(x 10-6
mol L-1
) from each formulated polymer after
dissolution studies.
127
Table 5.2 The thiol concentration (x 10-6
mol L-1
) at hour 2 of
stimulated gastric condition, hour 3 of stimulated
intestine condition and hour 70 of stimulated colon
condition Mean ± SD, N = 3. Incubation medium of
s colon condition containing polymer + bacteria (3)
is controlled sample.
129
Table 5.3 The thiol concentration (x 10-6
mol L-1
) of different
incubation medium at hour 70 in simulated colon
condition. Mean ± SD, N = 3. Incubation medium
containing polymer + bacteria (3) is controlled
sample.
130
Table 5.4 The statistical analysis results of thiol concentration
(x 10-6
mol L-1
) of various molar combinations of
polymers at incubation time of 5, 30, 70 hours in
simulated colon condition containing Bacteroides
fragilis. Mean ± SD, N =3.
131
xii
LIST OF FIGURES
Figure 1.1 Structure of the colon (large intestine) (after
Wikipedia, 2014).
3
Figure 1.2
Concentration of microflora in different regions of
gastrointestinal tract. 5
Figure 1.3 Mechanism of enzymatic reduction of sulphasalazine
in the colon.
14
Figure 1.4 Molecular structure of new-generation prodrugs of 5-
ASA.
15
Figure 1.5 TFA deprotection of triphenylmethyl (a) and
TFA/TES scavenger deprotection of triphenylmethyl
(b).
23
Figure 1.6 Disulphide bond formation by oxidation using
DMSO (R2SO).
25
Figure 1.7 Proposed disulphide polymer network from
oxidation of solely trithiol monomers.
26
Figure 1.8 Proposed disulphide polymer network from
oxidation of trithiol and dithiol monomers.
27
Figure 2.1 FT-IR spectrum of (3). 41
Figure 2.2 FT-IR spectrum of (5). 43
Figure 2.3 FT-IR spectrum of (6). 45
Figure 3.1 FT-IR spectrum of polymer P10. 57
Figure 3.2 FT-IR spectrum of polymer P11. 58
Figure 3.3 FT-IR spectrum of polymer P12. 59
Figure 3.4 FT-IR spectrum of polymer P15. 60
Figure 3.5 FT-IR spectrum of polymer P21. 61
Figure 3.6
Figure 3.7
FT-IR spectrum of polymer P51.
Raman spectroscopy of polymer P15.
62
63
Figure 3.8 (a) Scanning electron micrograph of polymer P10 at
(i) 150X; (ii) 300X; (iii) 1000X; (b) scanning area
for EDX micrograph, (c) EDX micrograph of
polymer P10.
64
xiii
Figure 3.9 (a) Scanning electron micrograph of polymer P11 at
(i) 150X; (ii) 300X; (iii) 1000X; (b) scanning area
for EDX micrograph, (c) EDX micrograph of
polymer P11.
65
Figure 3.10 (a) Scanning (a) Scanning electron micrograph of polymer P12 at
(i) 150X; (ii) 300X; (iii) 1000X; (b) scanning area
for EDX micrograph, (c) EDX micrograph of
polymer P12.
66
Figure 3.11 (a) Scanning electron micrograph of polymer P15 at
(i) 150X; (ii) 300X; (iii) 1000X; (b) scanning area
for EDX micrograph, (c) EDX micrograph of
polymer P15.
67
Figure 3.12 (a) Scanning electron micrograph of polymer P21 at
(i) 150X; (ii) 300X; (iii) 1000X; (b) scanning area
for EDX micrograph, (c) EDX micrograph of
polymer P21.
68
Figure 3.13 (a) Scanning electron micrograph of polymer P51 at
(i) 150X; (ii) 300X; (iii) 1000X; (b) scanning area
for EDX micrograph, (c) EDX micrograph of
polymer P51.
69
Figure 3.14 SEM micrograph at 300 X of polymer P10 and
elemental maps for carbon (C), oxygen (O), sulphur
(S) and nitrogen (N) for the same region obtained by
EDX mapping.
70
Figure 3.15 SEM micrograph at 300 X of polymer P11 and
elemental maps for carbon (C), oxygen (O), sulphur
(S) and nitrogen (N) for the same region obtained by
EDX mapping.
71
Figure 3.16 SEM micrograph at 300 X of polymer P12 and
elemental maps for carbon (C), oxygen (O), sulphur
(S) and nitrogen (N) for the same region obtained by
EDX mapping.
72
Figure 3.17 SEM micrograph at 300 X of polymer P15 and
elemental maps for carbon (C), oxygen (O), sulphur
(S) and nitrogen (N) for the same region obtained by
EDX mapping.
73
Figure 3.18 SEM micrograph at 300 X of polymer P21 and
elemental maps for carbon (C), oxygen (O), sulphur
(S) and nitrogen (N) for the same region obtained by
EDX mapping.
74
Figure 3.19 SEM micrograph at 300 X of polymer P51 and
elemental maps for carbon (C), oxygen (O), sulphur
(S) and nitrogen (N) for the same region obtained by
75
xiv
EDX mapping.
Figure 3.20 Disulphide polymer network from oxidation of
trithiol monomers.
78
Figure 3.21 Disulphide polymer network from oxidation of
trithiol and dithiol monomers.
78
Figure 4.1 Chemical reduction of cystamine by zinc/acetic acid
(mean, n = 3).
87
Figure 4.2 Standard calibration curve of cystamine. 88
Figure 4.3 Chemical reduction curves of polymer P10 using
zinc/acetic acid.
89
Figure 4.4 Chemical reduction curves of polymer P11 using
zinc/acetic acid.
90
Figure 4.5 Chemical reduction curves of polymer P12 using
zinc/acetic acid.
91
Figure 4.6 Chemical reduction curves of polymer P15 using
zinc/acetic acid.
92
Figure 4.7 Chemical reduction curves of polymer P21 using
zinc/acetic acid.
93
Figure 4.8 Chemical reduction curves of polymer P51 using
zinc/acetic acid.
94
Figure 5.1 Thiol concentration as a function of dissolution time
for polymer P10 over 120 mins. Dissolution was
carried out in 0.1 mol L-1 hydrochloric acid
containing NaCl and pepsin powder. Mean ± SD, n
= 3.
109
Figure 5.2 Thiol concentration as a function of dissolution time
for polymer P11 over 120 mins. Dissolution was
carried out in 0.1 mol L-1
hydrochloric acid
containing NaCl and pepsin powder. Mean ± SD, n
= 3.
110
Figure 5.3 Thiol concentration as a function of dissolution time
for polymer P12 over 120 mins. Dissolution was
carried out in 0.1 mol L-1
hydrochloric acid
containing NaCl and pepsin powder. Mean ± SD, n
= 3.
111
Figure 5.4 Thiol concentration as a function of dissolution time
for polymer P15 over 120 mins. Dissolution was
carried out in 0.1 mol L-1
hydrochloric acid
containing NaCl and pepsin powder. Mean ± SD, n
112
xv
= 3.
Figure 5.5 Thiol concentration as a function of dissolution time
for polymer P21 over 120 mins. Dissolution was
carried out in 0.1 mol L-1
hydrochloric acid
containing NaCl and pepsin powder. Mean ± SD, n
= 3.
113
Figure 5.6 Thiol concentration as a function of dissolution time
for polymer P51 over 120 mins. Dissolution was
carried out in 0.1 mol L-1
hydrochloric acid
containing NaCl and pepsin powder. Mean ± SD, n
= 3.
114
Figure 5.7 Thiol concentration as a function of dissolution time
for polymer P10 over 180 mins. Dissolution was
carried out in Sørensen’s phosphate buffer pH 6.8
containing pancreas powder. Mean ± SD, n = 3.
115
Figure 5.8 Thiol concentration as a function of dissolution time
for polymer P11 over 180 mins. Dissolution was
carried out in Sørensen’s phosphate buffer pH 6.8
containing pancreas powder. Mean ± SD, n = 3.
116
Figure 5.9 Thiol concentration as a function of dissolution time
for polymer P12 over 180 mins. Dissolution was
carried out in Sørensen’s phosphate buffer pH 6.8
containing pancreas powder. Mean ± SD, n = 3.
117
Figure 5.10 Thiol concentration as a function of dissolution time
for polymer P15 over 180 mins. Dissolution was
carried out in Sørensen’s phosphate buffer pH 6.8
containing pancreas powder. Mean ± SD, n = 3.
118
Figure 5.11 Thiol concentration as a function of dissolution time
for polymer P21 over 180 mins. Dissolution was
carried out in Sørensen’s phosphate buffer pH 6.8
containing pancreas powder. Mean ± SD, n = 3.
119
Figure 5.12 Thiol concentration as a function of incubation time
for polymer P51 over 180 mins. Dissolution was
carried out in Sørensen’s phosphate buffer pH 6.8
containing pancreas powder. Mean ± SD, n = 3.
120
Figure 5.13 Thiol concentration as a function of incubation time
for polymer P10 over 70 hours period. Incubation
was carried out in Sørensen’s phosphate buffer pH
7.4 containing, ( ) Bacteroides fragilis and polymer
P10, ( ) polymer P10 only without bacteria, ( )
bacteria only without polymer P10 Mean ± SD, n =
3.
121
xvi
Figure 5.14 Thiol concentration as a function of incubation time
for polymer P11 over 70 hours period. Incubation
was carried out in Sørensen’s phosphate buffer pH
7.4 containing, ( ) Bacteroides fragilis and polymer
P11, ( ) polymer P11 only without bacteria, ( )
bacteria only without polymer P11 Mean ± SD, n =
3.
122
Figure 5.15 Thiol concentration as a function of incubation time
for polymer P12 over 70 hours period. Incubation
was carried out in Sørensen’s phosphate buffer pH
7.4 containing, ( ) Bacteroides fragilis and polymer
P12, ( ) polymer P11 only without bacteria, ( )
bacteria only without polymer P12 Mean ± SD, n =
3.
123
Figure 5.16 Thiol concentration as a function of incubation time
for polymer P15 over 70 hours period. Incubation
was carried out in Sørensen’s phosphate buffer pH
7.4 containing, ( ) Bacteroides fragilis and polymer
P15, ( ) polymer P11 only without bacteria, ( )
bacteria only without polymer P15 Mean ± SD, n =
3.
124
Figure 5.17 Thiol concentration as a function of incubation time
for polymer P21 over 70 hours period. Incubation
was carried out in Sørensen’s phosphate buffer pH
7.4 containing, ( ) Bacteroides fragilis and polymer
P21, ( ) polymer P11 only without bacteria, ( )
bacteria only without polymer P21 Mean ± SD, n =
3.
125
Figure 5.18 Thiol concentration as a function of incubation time
for polymer P51 over 70 hours period. Incubation
was carried out in Sørensen’s phosphate buffer pH
7.4 containing, ( ) Bacteroides fragilis and polymer
P51, ( ) polymer P11 only without bacteria, ( )
bacteria only without polymer P51 Mean ± SD, n =
3.
126
Figure 7.1 Molecular structure of 2,2’-thiodiethanethiol. 141
xvii
LIST OF SCHEMES
Scheme 1.1 Reaction of Ellman’s reagent with thiol. 29
Scheme 1.2 Disulphide exchange of Ellman’s mixed
disulphide with thiol.
29
Scheme 2.1 Synthesis of (triphenylmethyl) thioethylamine (3). 35
Scheme 2.2 Synthesis of N,N',N''-tris[2-
(tritylsulfanyl)ethyl]propane-1,2,3-tricarboxamide
(5).
36
Scheme 2.3 Deprotection process to yield N,N',N''-tris(2-
sulfanylethyl)propane-1,2,3-tricarboxamide (6).
37
Scheme 2.4 Attempted synthesis of N,N',N''-tris(2-
sulfanylethyl)prop-1-ene-1,2,3-tricarboxamide
(8).
39
Scheme 2.5 Proposed mechanism for the formation of amide
bond using EDC.
48
Scheme 2.6 Synthetic routes for preparing (6). 49
xviii
LIST OF ABBREVIATIONS
GI Gastrointestinal
IBD Inflammatory bowel disease
5-ASA 5-aminosalicylic acid
HEMA 2-hydroxyethyl methacrylate
MMA Methylmethacrylate
BMAAB bis(methacryloylamino)azobenzene
SHIME Simulated human intestinal microbial ecosystem
TFA Trifluoroacetic acid
TES Triethylsilane
DTNB 5,5’-dithiobis-2-nitrobenzoic acid
TNB2-
5-thio-2-nitrobenzoic acid
SEM Scanning electron microscopy
EDX Energy dispersive X-ray
TLC Thin layer chromatography
FT-IR Fourier transform infrared
NMR Nuclear magnetic resonance
1H-NMR Proton nuclear magnetic resonance
13C-NMR Carbon nuclear magnetic resonance
LC-MS Liquid chromatography-Mass spectroscopy
EDC N-(3-dimethylaminopropyl)-N’-ethylcarbodiimide
DMSO Dimethylsulphoxide
DCC N, N”-dicyclohexylcarbodiimide
DCM Dichloromethane
xix
DCU Dicyclohexylurea
HOBt 1-hydroxybenzotriazole hydrate
EDTA Ethylenediaminetetraacetic acid
WCAB Wilkens-Chalgren Anaerobic Broth
CMM Robertson’s cooked meat media
ANOVA One-way analysis of variance
HSD Honestly Significant Difference
s Singlet
d Doublet
t Triplet
m Multiplet
et al. et alii, others
h. hour
min minute
Rf Resolution factor
ml Milliliter (s)
MHz Mega Hertz
oC Degree Celsius
L Liter
mm Millimeter
xx
SINTESIS, PENCIRIAN DAN PENILAIAN SECARA IN VITRO BAGI
POLIMER DISULFIDA BERANGKAI-SILANG SEBAGAI
PENGANGKUTAN BERPOTENSI UNTUK SISTEM PENYAMPAIAN UBAT
KHAS KEPADA KOLON
ABSTRAK
Sistem penyampaian drug ke kolon adalah sangat berguna untuk menyampaikan drug
untuk rawatan penyakit kolon setempat seperti penyakit keradangan usus, ulser
kolitis dan penyakit Crohn. Polimer disulfida berangkai-silang telah mendapat
perhatian kerana keupayaannya untuk bertindak sebagai polimer sensitif redoks dan
ikatan disulfida hanya akan dilekangkan oleh persekitaran yang mempunyai potensi
redoks yang rendah di dalam kolon. Kebelakangan ini, polimer rantai bercabang
disulfida telah menerima perhatian yang lebih disebabkan oleh hakikat bahawa
polimer ini kurang terdedah untuk degradasi dalam keadaan pH rendah di perut
berbanding dengan polimer rantai linear disulfida. Oleh itu, tujuan kajian ini ialah
untuk mensintesiskan monomer trithiol berasaskan asid trikarbalilik untuk
pempolimeran ke polimer rantai bercabang disulfida. Polimer sintetik telah dicirikan,
dikaji secara kimia dan dinilai dengan menggunakan kajian disintegrasi secara in
vitro. Monomer ini telah disintesiskan melalui tindak balas gandingan amida antara
asid trikarbalilik dan (trifenilmetil) thioetilamina dengan menggunakan dua langkah
sintesis. Monomer tersebut dinyahlindungkan dengan menggunakan asid
trifluoroasetik dan trietilsilana untuk mendedahkan atom sulfur dalam persediaan
untuk pempolimeran selanjutnya. Serbuk pepejal putih diperolehi dengan hasil
xxi
lebih kurang 20-25%. Keputusan spektroskopi dan analisis unsur CHNS
mengesahkan monomer yang dikehendaki. FT-IR menunjukkan kehadiran puncak
amida dan disokong oleh analisis jisim menggunakan LC-MS. Pempolimeran secara
pengoksidaan N,N',N''-tris(2-sulfaniletil)propana-1,2,3-trikarboksamida (monomer
trithiol) dan 2,2'- (etilenadioksi)dietanathiol (monomer dithiol) dengan pelbagai
nisbah molar menghasilkan enam (6) polimer yang berbeza, dinamakan, P10, P11,
P12, P15, P21 dan P51. Spektroskopi Raman menunjukkan kemunculan ikatan
disulfida. Kajian reduksi kimia menunjukkan bahawa semua polimer disulfida telah
diturunkan dengan lengkapnya selepas 1 jam dengan kepekatan thiol yang berbeza.
Dalam keadaan simulasi gastrik dan usus kecil, semua polimer menunjukkan
kepekatan thiol yang rendah jika dibandingkan dengan kepekatan thiol yang dikesan
dalam keadaan simulasi kolon dengan kehadiran Bacteroides fragilis. Keputusan ini
membuktikan bahawa semua polimer disulfida dapat bertahan dalam persekitaran
gastrik dan usus kecil yang kasar dan degradasi hanya akan berlaku dengan
kehadiran bakteria anaerobik di kolon. Degradasi didapati lebih ketara dalam
polimer P15 menunjukkan kepekatan thiol yang tertinggi, iaitu 57 x 10-6
mol L-1
berbanding polimer yang lain. Keputusan ini memberi persetujuan umum bahawa
biodegradabiliti bergantung pada kebolehkembangan polimer-polimer ini dalam
keadaan akues. Penyelidikan ini telah mengidentifikasikan polimer berangkai silang
disulfida yang mungkin mempunyai potensi untuk sasaran ke kolon. Walau
bagaimanapun, kajian selanjutnya diperlukan bagi mencapai kestabilan dan
penggunaannya sebagai polimer dalam bentuk dosaj farmaseutikal.
xxii
SYNTHESIS, CHARACTERISATION AND IN VITRO EVALUATION OF
DISULPHIDE CROSS-LINKED POLYMERS AS POTENTIAL CARRIERS
FOR COLON SPECIFIC DRUG DELIVERY SYSTEM
ABSTRACT
Colon drug delivery system is very useful to deliver drugs for treatment of localised
colonic diseases such as inflammatory bowel disease, ulcerative colitis and Crohn’s
disease. Disulphide cross-linked polymer has received much attention because of its
ability to act as a redox sensitive polymer and will only be cleaved by the low redox
potential environment in the colon. Recently, branch-chained disulphide polymers
had received more attention due to the fact that it is less susceptible for degradation
in low pH condition of the stomach compared to linear-chained disulphide polymers.
Therefore, the aim of this work is to synthesise tricarballylic acid based trithiol
monomer for polymerisation into branch-chained disulphide polymers. The
synthesised polymers were characterised, studied chemically and evaluated using in
vitro disintegration studies. The monomer was synthesised by amide coupling
reaction between tricarballylic acid and (triphenylmethyl) thioethylamine by using
two synthetic steps. The monomer was deprotected using trifluoroacetic acid and
triethylsilane to expose the sulphur atoms in preparation for further polymerisation.
White powdery solid was obtained with yield around 20-25%. Spectroscopic and
CHNS elemental analysis results complemented with the desired monomer. FT-IR
showed the presence of amide peaks and supported by the mass analysis using LC-
MS. The oxidative polymerisation of N,N',N''-tris(2-sulfanylethyl)propane-1,2,3-
tricarboxamide (trithiol monomer) and 2,2’-(ethylenedioxy)diethanethiol (dithiol
xxiii
monomer) of various molar ratios resulted six (6) different polymers, namely, P10,
P11, P12, P15, P21 and P51. Raman spectroscopy demonstrated the emergence of
disulphide bond. Chemical reduction studies showed that all the disulphide polymers
were completely reduced after 1 hour of reduction with different thiol concentrations.
In simulated gastric and intestinal condition, all the polymers showed low thiol
concentrations when compared to the detected thiol concentrations in simulated
colon condition with the presence of Bacteroides fragilis. The results proved that all
the disulphide polymers were able to withstand the harsh environment of the gastric
and intestinal condition and degradation will only occur in the colon condition with
the presence of anaerobic colonic bacteria. Disintegration was found to be more
pronounced in polymer P15 as the highest thiol concentration of 57 x 10-6
mol L-1
among all the other polymers. This result correlated the general consensus that
biodegradability relies on the swelling ability of polymers in an aqueous environment.
This work has successfully identified a disulphide cross-linked polymer, which might
be potential for colon specific targeting. However, further study on these polymers is
required to establish the stability and use of the polymer within a pharmaceutical
dosage form.
1
CHAPTER ONE
INTRODUCTION
1.1 Background
To date, oral drug delivery is the most preferred, common, convenience and widely
accepted route among many other routes of drug administration (Rubinstein, 1995;
Laura et al., 2011). Upper gastrointestinal (GI) tract appeared to be the major region
for dissolution and absorption of orally administered drug. However, this approach
is not suitable for drugs to be absorbed in lower GI tract or advanced biotechnology
products such as peptides and proteins, whereby undesirable side effects and
treatment failure will occur. Therefore, studies had been done in developing specific
drug targeting especially to lower GI tract. Colon specific drug delivery had
received much interest with much work already been carried out in this area of drug
delivery (Yan et al., 2010; Kenawy et al., 2011; Ursekar et al., 2012; Lim et al.,
2013). The role of colon specific drug delivery is not only limited for localised
treatment but also crucial for systematic treatment (Tozer et al., 1995). Although
colon specific drug delivery can also be achieved via rectal route but this route
appeared to be less readily accepted and less appealing to patients. Moreover, study
showed that it is difficult to deliver drug to the proximal colon via the rectal route
(Ritschel, 1991).
Colon specific drug delivery is particularly important in localised treatment of colon
diseases such as inflammatory bowel disease (IBD), ulcerative colitis, Crohn’s
2
disease and colorectal cancer (Gupta et al., 2001; Rubinstein, 2005; Yan et al., 2010).
The nature of colon which is less hostile has a near neutral pH and lower activity of
peptidase enzyme favours the systemic absorption of protein and peptide drugs
(Maroni et al., 2012).
1.2 Anatomy of the colon
The GI digestive tract is a system of organs in human which responsible in taking
food, digesting it to extract energy and nutrients and eliminating waste. The normal
human adult male GI tract consists of the upper and lower GI tracts and is
approximately 6.5 meters long (Anthea et al., 1993).
The colon, or large intestine, is located at the distal end of the GI tract (Figure 1.1).
It is a muscular tube with a length of approximately 1.5 m long, has an average
diameter of approximately 6.5 cm, with a diameter that varies from 2 cm in the
sigmoid colon to 9 cm in the caecal region, running from the ileocaecal valve to the
anus (Cummings and MacFarlane, 1991). The human colon is composed of the
caecum, ascending segment, transverse segment, descending segment and sigmoid
region. Colon plays an important role in extracting water and salt from solid wastes
before they are eliminated from the body, storing waste, absorbing some vitamins
and providing a site for flora-aided fermentation. Unlike the small intestine, the
colon does not play a major role in absorption of foods and nutrients. Colon does not
have villi although it does demonstrate crescentric folds, which increase the internal
surface area of the colon to approximately of 1300 cm2 (Cummings and MacFarlane,
1991). Guinea pigs and rodents models were commonly used in the study of colonic
3
drug delivery (Friend, 1991). However, there are differences between the animal
models with normal human. The guinea pig has a very large caecum whereas
humans have a poorly defined caecal region continuous with the colon (Friend, 1991).
The transit time was found to be shorter in guinea pigs and slightly longer in rats if
compared to humans (Pettersson et al., 1976). The mucosa of the colon is lined
almost entirely by goblet mucus secreting cells, whereby the large amount of
bicarbonate ions from the mucus maintains the basic pH of the colonic region
(Binder and Sandle, 1994).
Figure 1.1 : Structure of the colon (large intestine) (after Wikipedia, 2014).
4
1.3 Microflora of the gastrointestinal tract
The upper GI tract is sparsely populated with micro-organisms. The acidic
environment of the stomach exhibits a strong bactericidal activity, whereby the
microbial concentration is usually less than 103 cfu/ml (Ilett et al., 1990). Acid-
tolerant micro-organisms such as gram-positive aerobic streptococci and lactobacilli
are the main inhabitants in the stomach (Hao and Lee, 2004). The upper two-thirds
of the small intestine which includes duodenum and jejunum contain similar bacterial
concentration to the stomach, between 103 to 10
4 cfu/ml. However, gram-negative
bacteria begin to outnumber gram-positive bacteria in the distal ileum. The reduction
in acidity and lower redox potentials play a major role in maintaining a more diverse
microflora and higher bacteria population (Tannock, 1983).
Colon is the primary site of microbial colonisation in human body. The colon
contains a very large quantity of bacteria from various species. The bacterial
concentration in the colon is around 1011
to 1012
cfu/ml and approximately one third
of the fecal dry weight consists of bacteria (Simon and Gorbach, 1984). The increase
in bacterial concentration in this region is due to a near neutral pH caused by
neutralisation of the bowel contents by intestinal juice and lower motility rate of the
colon. However, 99.9 % of colonic microflora is obligate anaerobes (Hao and Lee,
2004). There are over 400 different bacterial species found in the colonic region.
The predominant species isolated include Bacteroides, Eubacterium, Bifidobacterium
(Hill and Drasar, 1975). Anaerobic gram-positive Cocci, Enterococci, Clostridia and
other species of Enterobacteriaceae, Coliforms, Staphylococci, Lactobacillus,
Spirochetes, Pseudomonas, Proteus, Clostridium, Actinomyces, Borrelia,
5
Fusobacterium and Diphtheroides species are also found. However, Bacteroides
species account for nearly 32 % of all bacterial flora isolated from the GI tract
(Finegold et al., 1977). The comparison of microbial concentration in different
regions of GI tract is shown in Figure 1.2.
Figure 1.2 : Concentration of microflora in different regions of gastrointestinal tract
(taken with modification from Basit, 2005).
Certain diseases or antibiotic treatment will influence the microbial flora in the gut
(Friend and Tozer, 1992). The nature of certain disease, where reduction of gastric
acid secretion occurred, will lead to increase in bacterial growth in the stomach
(Rowland, 1988). The speed of peristalsis movement decreases from the jejunum to
upper ileum and the distal ileum. As it is approaching the ileo-caecal valve,
peristalsis slows down to an almost stagnant state and this has been the major factor
which cause the drastic rise in the bacterial population in this area. The bacteria
6
populations found in this area are mainly Bacteroides, Enterobacteria and
Bifidobacteria. Huge changes of some organisms in the region within the gut can
occur when antibiotic treatments are introduced where it has bactericidal effect and
suppresses the bacterial growth (Goldin and Grobach, 1977).
Colon is well known for its reductive environment, where the redox potential
becomes more negative from the small intestine to the large bowel. The redox
potential of proximal small bowel is -67 ± 90 mV, -196 ± 97 mV in the distal small
bowel and -415 ± 72 mV in the colon (Stirrup et al., 1990). The presence of the
bacterial microflora causes the changes in the redox potential along the GI tract. Due
to its low redox potential, the colonic region is very active in reductive and
degradative reactions (Rowland, 1986).
Bacterial microflora in the GI tract produce a wide range of reductive and hydrolytic
enzymes which include β-glucoronidase, β-galactosidase, β-xylosidase, azoreductase,
nitroreductase, urea hyroxlase and α-arabinosidase (Kinget et al., 1998). The ability
of colonic anaerobic bacteria to produce appropriate digestive enzyme in order to
digest the constantly changing carbohydrates complex was exploited for the
development of enzyme-sensitive prodrugs to achieve colonic drug targeting (Sinha
and Kumria, 2001a; Sinha and Kumria, 2001b).
7
1.4 Colon-specific drug targeting
The concept of delivering drug to the desired site is not new. All drugs exert their
beneficial effects along with undesirable side effects to varying degrees of severity.
Therefore, site-specific drug delivery is important by enhancing the beneficial effects
and limiting the side effects. The formulated dosage form for colon-specific drug
delivery must pass through the upper GI tract intact before delivering the drug to the
colonic region.
Physiological factors in the upper GI tract such as extreme acidity in stomach,
degradative enzyme activities and presence of bile salts will destroy the drug
molecules that are intended to colon, especially peptides and proteins. This will
result in poor bioavailability of drugs and treatment outcome. Due to the barriers of
the upper GI tract, colon has been focused as the targeting site for orally
administered drug. Numerous investigations have shown that some anti-
inflammatory (Wilson and Washington, 1989) and antidiabetic (Gleiter et al., 1985)
drugs are better absorbed from the colon rather than the upper GI tract.
The colon is found to have prolonged residence time for the colonic contents (Coupe
et al., 1991). The average transit time through the colon is 22-36 hours and it is
much higher if compared to the transit time in the stomach (0.5-3 hours) and the
small intestine (1-6 hours) (Coupe et al., 1991). On top of that, colonic transit time
has been shown to be independent of size and density of the dosage form (Parker et
al., 1988). The ideal property for a colon-specific drug delivery system is to spend
as little time as possible in the upper GI tract (Friend, 1991). Therefore, the
8
prolonged colonic transit time provides a longer time interval for drug absorption in
the colonic region. This will compensate the smaller surface area for absorption in
the colon compared to the small intestine.
1.5 Strategies for targeting drugs to the colon
The main responsibility of a colonic drug delivery system is to utilise the special
characterisitics of the colon in order to achieve localised drug release. The main
concept of orally administered colon-specific drug delivery is where the dosage form
must be able to withstand the harsh environment of the stomach and small intestine
but to achieve drug release in the colon. The major characteristics of the GI tract
include pH, transit time, enzymes, bacteria and pressure (Basit, 2005; Bhalerao and
Patel, 2012) were taken into considerations in order to develop a good formulation
for colonic drug delivery. These strategies are currently being studied and will be
further discussed below.
1.5.1 pH responsive delivery
pH in human GI tract changes when it shifts from one region to another. The
environment of the stomach is acidic (pH 1-2) and the pH increases in the small
intestine region (pH 6.5-7). The pH in the terminal ileum and colon (pH 7-8) is the
highest in the human GI tract. The concept of pH responsive delivery was designed
by using materials that are insoluble in acidic pH but dissolve in neutral to slightly
basic pH (Ibekwe et al., 2006). However, pH in the terminal ileum region is higher
than in the caecum. Thus, the dosage forms are often delayed at the ileocecal
9
junction. In short, the concept of using polymers that are sensitive to higher pH was
employed and adapted for colonic drug delivery instead of conventional enteric
coating (Edsbacker and Anderson, 2004).
Acrylic polymers from the Eudragit® range are commonly used for this purpose
because of its solubility when expose to pH above 6 (Basit, 2005). Eudragit-based
polymers can be made to dissolve at various basic pH by modifying the methylester
content (Peeters and Kinget, 1993). Eudragit® S and Eudragit® L were designed to
be specifically dissolved in pH 7 and pH 6 respectively. Dew et al. (1982) were the
first to employ Eudragit® S as a capsule coating by utilising gastrointestinal pH as a
trigger for drug release in the distal gut. The results were positive in most patients as
the capsule disintegrated in the distal gut. However, Ashford et al. (1993a, 1993b)
found that the drug release of Eudragit® S-coated tablets in the colon of healthy
volunteers was not adequately reproducible. The reason behind was due to the
decrease in pH after passage through the ileocaecal valve. Therefore, Eudragit® S
coating dissolves and releases its drug content in the ileum rather than colon.
Despite such evidence of premature release of drug contents in the ileum,
preparations include Asacol® (Eudragit® S) and Claveral
® (Eudragit® L) have been
formulated using which have approval for human use. The preparations were found
to be successful in treatment of IBD (Hardy et al., 1987). In order to compensate the
low release pH of Eudragit® L, a thicker layer was formulated. The release of drug
contents (5-aminosalycilic acid) from both preparations is reported to take place at
the distal ileum and right colon.
10
1.5.2 Time responsive delivery
The size, shape and density of the dosage form and the feed status of the individual
are the major factors which will affect the GI transit time (Davis et al., 1984;
Devereux et al., 1990). Residence time in the stomach varies from a few seconds to
few hours. However, small intestine transit time was found to be more consistent at
3-4 hours, without being affected by feed status of the individual (Davis et al., 1986).
The consistent transit time of small intestine has been exploited in developing colon
drug delivery system. Time responsive delivery is formulated to release their drug
contents after a predetermined lag time. Assumption was made by researchers,
whereby 5-6 hours are needed for the ingested dosage form to reach the colonic
region. Therefore, a nominal lag time of 5 hours is usually considered sufficient
(Davis et al., 1986).
The pioneer time responsive delivery system was developed by Wilding et al. (1992),
namely, PulsincapTM
device. The device consists of an impermeable hard gelatin
capsule sealed at one end with hydrogel plug. Upon contact with gastrointestinal
fluid, the plug hydrates and begins to swell and after a pre-set lag time, ejects from
the capsule body, enabling drug release to occur. The size and composition of the
plug are crucial in controlling the lag time of the entire device. Two different
PulsincapTM
devices with different pre-set lag time of 5 and 6 hours respectively
were studied in fasted human subjects using gamma scintigraphy (Hebden et al.,
1999). The authors found that the location of the device varied in human body at the
time of release. Further study reported that the device exhibits poor emptying feature
11
especially in distal bowel. Lack of fluid in the distal bowel appeared to be the major
factor which caused the drawback (Wilding, 2000).
Newer colon drug delivery system was described by merging of both pH and time
responsive mechanisms in order to increase the effectiveness (Ishibashi et al., 1998).
The system comprises of a conventional hard gelatin capsule which contains mixture
of drug content and organic acid. The outer surface of the capsule is coated with
three layers, including outer enteric layer, hydrophilic layer and acid-soluble layer.
The entire system was designed to survive in the harsh condition of the stomach.
Subsequently, the capsule will reach a higher pH condition in the small intestine,
whereby the outer enteric layer will dissolve followed by the intermediate
hydrophilic layer. The inner acid-soluble layer which dissolves at pH below 5 will
survive the condition of the intestine. However, fluid will enter the capsule and lead
to the dissolution of the organic acid. pH reduction occurs followed by the
dissolution of the acid-soluble layer, leading to drug release from the entire system.
Study was done on fasted and fed volunteers but the results showed variability for
the site of disintegration (Ishibashi et al., 1998).
From the report of several studies, individual variability is a major influence towards
the gastrointestinal transit time (Coupe et al., 1991). Moreover, transit was found to
be faster in the morning if compared to the evening (Hebden et al., 1999). Time
responsive delivery system was unable to detect individual’s gastrointestinal transit,
which limits the practicality of the formulation.
12
1.5.3 Pressure responsive delivery
Higher pressures are encountered in the colon as a result of peristalsis movement.
The grinding, propulsion and motility of the luminal contents were found to be
generating pressure due to the muscle contraction of the intestinal wall. However,
the intensity and duration of the generated pressure varies throughout the GI tract
(Takaya et al., 1995). The colon is believed to exert a higher effective luminal
pressure in a viscous environment. A capsule utilising pressure responsive system
was developed by Takaya et al. (1995), using a hydrophobic polymer ethycellulose.
Drug release can be achieved after the successful disintegration of the capsule due to
the luminal pressure of the colon. The thickness of the ethylcellulose layer plays a
crucial role for the disintegration of the dosage form.
Several works had been done on methods of manufacturing pressure responsive
delivery system. Takaya et al. (1995) had successfully coated the inner surface of
the gelatin capsule with hydrophobic ethylcellulose, Hu et al. (2000) reported a low
temperature coating of the capsule-shaped pieces of suppository base. The dipping
method into both ethanolic ethylcellulose and alkalised enteric polymer solution was
conducted by Jeong et al. (2001). Investigations were made for these formulations
which involved pharmacokinetic evaluation. Correlation between times for
appearance of drug in plasma with literature values for colon arrival times had been
done. However, the results did not conclusively show successful disintegration in
the colon due to gastric and intestine transit times are known to be variable.
13
1.5.4 Bacteria responsive delivery
Majority of the bacteria in the human colon are anaerobic in nature. These anaerobic
bacteria are responsible in producing various types of enzyme to metabolise
substrates, such as proteins and carbohydrates, which escape from the upper GI tract
(Cummings et al., 1989). Materials which are susceptible to the enzymatic
degradation in the colon but able to survive the condition of gastric and small
intestine, could be designed as carriers for colonic drug targeting. These enzyme
sensitive materials depend heavily on the enzyme-generating microflora in the colon.
The enzymes generated include azoreductase, peptidase, esterase and glycosidase.
To date, bacteria responsive colon drug delivery has received much attention
(Vandamme et al., 2002; Sinha and Kumria, 2003; Chourasia and Jain, 2004; Ibekwe
et al., 2008).
1.5.4.1Azo-containing prodrugs
Sulphasalazine appeared to be the first bacteria responsive colon drug delivery
system being invented. It is a prodrug consisting of the active drug content
(mesalazine) linked by an azo bond to a carrier molecule (sulphapyridine)
(Peppercorn and Goldman, 1972; Svartz, 1988). From the study done by Myers et al.
(1987), mesalazine was found to be rapidly absorbed from the small intestine.
However, absorption is inhibited in the gastric and small intestine until it reaches
colon when the prodrug is ingested. Bacteria in the colon will release enzyme such
as azo-reductase to cleave the azo bond of the prodrug, leading to release of the
active drug content of 5-aminosalicylic acid (5-ASA) at the inflammation region.
14
Klotz (1985) reported that approximately 85% of an orally administered
sulphasalazine survived unabsorbed into the colonic region.
Enzymatic reduction will break down sulphasalazine into 5-aminosalicylic acid (5-
ASA) and sulphapyridine as shown in Figure 1.3. 5-ASA is generally unabsorbed in
the colon where it is responsible in providing topical anti-inflammatory activity
(Peppercon, 1984). However, sulphapyridine is well absorbed in the colon (Klotz,
1985) and causes undesirable side effects such as allergic reactions, which occurs in
up to 50% of recipients.
Figure 1.3 : Mechanism of enzymatic reduction of sulphasalazine in the colon.
Sulphasalazine
Enzymatic reduction
5-aminosalicylic acid Sulphapyridine
15
In order to solve the toxicity issue of sulphapyridine, mesalazine has been azo
bonded to another mesalazine molecule, namely olsalazine (Campbell and Berlingdh,
1998) or inert carrier, namely balsalazide and ipsalazide (Chan et al., 1983).
Molecular structures of olsalazine, balsalazide and ipsalazide are shown in Figure 1.4.
These methods provide alternative prodrugs for use in IBD which can prevent the
toxicity problem of sulphapyridine.
Figure 1.4 : Molecular structure of new-generation prodrugs of 5-ASA.
Olsalazine
Balsalazide
Ipsalazide
16
1.5.4.2 Azo-polymers
Azo-reductase is a type of enzyme which is commonly found in human colon. The
use of bacterial azo-reductase to split prodrug sulphasalazine into sulphapyridine and
5-ASA was the first colon specific targeting system. Subsequently, several studies
were carried out by exploiting the azo-reductase enzyme as a release mechanism for
drugs within the colonic region. Coating of peptide insulin with polymers cross-
linked with azoaromatic group has been discovered to protect insulin from the harsh
environment of stomach and small intestine. Thereafter, azo bonds were reduced in
the colon, leading to the release of insulin (Saffran et al., 1986). Further study was
conducted to deliver similarly coated insulin dosage forms to the colon of diabetic
dogs (Saffran et al., 1990) and the release mechanism was concluded to be caused by
the enzymatic degradation of the azo-polymer coatings in the colon. The increase in
insulin level and reduction in glucose production and glucose level were found to be
statistically significant.
Copolymers were employed for potential colon drug targeting by Van den Mooter et
al. (1992, 1993 and 1995). Copolymers composing of 2-hydroxyethyl methacrylate
(HEMA) and methylmethacrylate (MMA) were prepared in the presence of a
bifunctional azo compound, which is bis(methacryloylamino)azobenzene (BMAAB).
Different molar ratios of HEMA and MMA were used in order to obtain different
copolymers. Copolymer comprised of 1:6 molar ratio of MMA/HEMA and polymer
without the addition of MMA showed significant bacterial reduction both in vitro
and in vivo. Both of the polymers demonstrated good resistant in simulated gastric
17
acid and intestinal fluid. Conclusions were made that the monomer composition has
a greater influence than the structure of the cross-linking agent.
Hydrophilic azo-polyamides were studied as a potential colonic drug targeting by
Schact et al. (1991). The films were found to be completely dissolved under
reductive medium (-430 mV) and simulated human intestinal microbial ecosystem
(SHIME). The degradation was detected by observing the colour changes from pink-
orange to white/colourless. Lloyd et al. (1994) suggested that complete reduction of
azo bonds to amine would be favorable for effective drug release. Hydrophilic
polymers appeared to meet the requirement because of reduction of such polymers
are reported to go toward amine formation. Meanwhile, hydrophobic polymers
reduction stops at the hydrazo stage which appeared to be undesirable (Schact et al.,
1996). Recent studies showed similar results in degradation of azo dyes by bacteria
(Pandey et al., 2007; Hong et al., 2008).
1.5.4.3 Glycosidic prodrugs
Colonic bacteria provide glycosidase activity by generating glycosidase enzyme
which forms the fundamental of a colon specific drug delivery system. Friend and
Chang (1984 and 1985) utilised corticosteroid prodrugs as glycosidic carrier by the
attachment of the active agent. Drug glycosides are poorly absorbed from small
intestine due to its hydrophilic nature. The drug glycosides can be cleaved by
glycosidase enzyme upon reaching colonic region, releasing the active drug contents
which will be absorb by the colonic mucosa. Several studies have reported that
18
absorption occur for corticosteroids obtained from hydrolysis of glycosidic prodrug
in the colonic region.
Strategy of glycosidic prodrug was evaluated in rats with two steroid prodrugs,
prednisolone 21-β-D-glucoside and dexamethasone 21-β-D-glucoside (Tozer et al.,
1991). The potential of glycosidic prodrug is assessed by determining the rates of
its hydrolysis down the alimentary canal of the guinea pig. It was found that the
caecum and colon contents showed greater hydrolytic activity than the stomach and
small intestine contents. On top of that, the movement and hydrolysis of the prodrug
down the GI tract of the guinea pig were also examined. The authors reported
approximately 20 to 30 % of an oral dose appeared to reach the caecum, whereby the
prodrug was rapidly hydrolysed to the active form. Greater site-specific delivery is
expected for human due to less glucosidase activity in the small intestine.
1.5.4.4 Polysaccharides
Natural or synthetic polysaccharides have received much attention for colon specific
drug delivery. The feature of natural polysaccharides which can be degraded by the
local bacterial enzyme upon entering colonic region was exploited for colon drug
delivery (MacFarlane and Cummings, 1991). These natural polysaccharides are
present in normal dietary food and usually are resistant to digestive enzyme in the
upper GI tract. Many of these polymers are already used as pharmaceutical
excipients in formulations. Therefore, problems associated with toxicity and
biocompatibility are much simplified. However, the hydrophilic nature of the
polysaccharides would cause swelling in the upper GI tract and eventually lead to
19
premature drug release. Thus, methods were developed to prevent premature drug
release by either chemically modified the polymers and mixed with hydrophobic
polymers. This will prevent the swelling in the upper GI tract, but still retaining the
solubilisation feature of the coating in the colon due to bacterial degradation.
Several studies have been done on the use of dextrans in colonic drug delivery
(Harboe et al., 1988; McLeod et al., 1993). Dextran has potential to act as a carrier
for drugs such as naproxen and dexamethasone. The authors reported that
degradation of dextran was significantly higher in colon if compared to upper GI
tract. Modification has been made for dextran by esterification with fatty acids in
order to reduce its solubility (Hirsch et al., 1995). In vitro degradation studies
showed that the modified dextran resisted the harsh condition of the upper GI tract,
but sensitive to degradation by colonic microflora. However, increment in degree of
crosslinking will render the reduction of colonic degradability of the polymer.
Pectinolytic enzymes found in the colonic region are responsible in the degradation
of pectin (Rubinstein and Sintov, 1992). This unique feature was exploited by the
researchers which pectin was used as a carrier for colonic drug delivery (Ashford et
al., 1994). Pectin Type 170 (30-40 % methoxylated) and Pectin USP (70 %
methoxlated) were used as a compression coating. A minimum thickness of 0.9 mm
(700 mg) of Pectin USP coat was found to be viable in resisting the intestinal
condition. However, a thicker coat of 1000 mg showed poor degradation in
pectinolytic enzyme medium due to poor penetration of fluid to hydrate the coating
for enzyme entry. From the scintigraphic result, pectin coating is able to protect the
20
drug until colonic region and majority of the release occurred in caecum and
ascending colonic region. Modification was made by cross-linking calcium with
pectin, yielding calcium pectinate (Adkin et al., 1997). The authors reported that
calcium pectinate tablets were degraded in rat caecum, whereby such modification
has potential for colonic drug delivery.
Guar gum is a galactomannan which has high viscosity. This polysaccharide has
potential to be used as a carrier, delivering drugs to the colon without undesirable
release in the upper GI tract. The potential of guar gum has been studied in the form
of a matrix and compression coat (Rubinstein and Gliko-Kabir, 1997; Krishnaiah et
al., 1998a and 1998b; Tugcu-Demiroz et al., 2004). A study utilising guar gum
compression coat of 400 mg that applied to tablet cores of 300 mg, containing 250
mg of ornidazole was found to be significantly delay the onset of drug release and
absorption (Krishnaiah et al., 2003). However, the drug from the coated formulation
was found to be absorbed in a slower rate from the colon.
Amylose is one of the major components of starch, apart from amylopectin
(Biliaderis, 1991). Amylose is susceptible to fermentation by a broad range of
colonic bacteria (Salyers et al., 1977), where more than half of the bacterial
population is able to digest amylose (MacFarlane and Englyst, 1986). The
polysaccharide amylose has been exploited as a carrier for colonic drug delivery in
the form of film coating (Siew et al., 2000; Leong et al., 2002). Addition of
hydrophobic ethylcellulose as a structuring agent is essential due to the fact that
amylose films tend to swell in aqueous media. Various ratios of amylose with
21
ethylcellulose were employed to investigate the applicability in colonic drug delivery.
Drug release from the coated formulations was reported in fermentation environment
of the colon. Therefore, amylose coated formulations have potential to become a
carrier for drug delivery to the colon.
1.5.4.5 Disulphide polymers
To date, disulphide polymers have received much interest due to its potential as
carrier for colonic drug delivery. Disulphide polymer was found to be resistant in the
upper GI tract but susceptible to degradation in the colonic region. Low redox
potential environment of the human colon is the key feature for the entire mechanism,
where disulphide bond will be reduced. It has been proposed that linear polymers
containing disulphide backbones could be degraded in the low redox potential
environment of the human colon (Schact and Wilding, 1991). Watts and Illum (1997)
reported that the tablets coated with polymer rapidly disintegrated, achieving
complete dissolution in the testing medium.
Recently, studies were focused on employing branch-chained disulphide polymers
instead of linear-chained. The major reason was due to the insolubility features of
the branch-chained polymers. Linear-chained polymers are easily degraded in low
pH condition and more soluble if compared to branch-chained polymers (Sahudin,
2001; Lim et al., 2013). The ability of disulphide polymers to degrade in low redox
potential of the colonic environment while sustaining the harsh environment of the
upper GI tract, have been exploited as a redox-sensitive polymers in colon-specific
drug delivery.
22
1.6 Literature review
Protection of the thiol group is crucial in many areas of organic research especially in
peptide synthesis. The thiol groups were found to be very reactive and therefore the
protection is necessary for the sulphur atom. A free thiol group can be protected as a
thioether or thioester. The protecting group can be easily cleaved via acidic
hydrolysis or by using sodium/ammonia (Wuts and Greene, 2006). Triphenylmethyl
thioether protecting group which is used in this synthesis can be remove by using
iodine, thallium trifluoroacetate and trifluoroacetic acid (TFA). Iodine and thallium
are not favorable as a deprotection agent because they will effect simultaneous
disulphide bond formation (Fields and Noble, 1990). Relatively, TFA is a more
favorable agent because it generates free thiol groups without forming disulphide
bond (Atherton and Sheppard, 1987). However, the using of TFA alone for the
deprotection procedure is not sufficient. The cleavage reaction is reversible due to
the high stability of the trityl cation and strong nucleophilic nature of the thiol group.
Hence, the use of triethylsilane (TES) scavengers appeared to be crucial in the
deprotection process. TES will quench the trityl carbocation to form
triphenylmethane and make the entire process irreversible (Figure 1.5) (Pearson et.al.
1989).
23
a)
b)
Figure 1.5 : TFA deprotection of triphenylmethyl (a) and TFA/TES scavenger
deprotection of triphenylmethyl (b).
TFA
Trityl protected thiol
Thiol
Trityl cation
Trityl protected thiol
Thiol
TFA/Et3SiH
Et3SiOCOCF3 +
Triphenylmethane
24
Linear disulphide polymers have been studied shown to be biodegradable in colonic
bacterial culture (Le, 1998). Such polymers have been suggested as the coating
materials for colon drug delivery system (Schacht and Wilding, 1991). However,
linear-chained disulphide polymers were found to be easily degraded in low pH
condition of the stomach (Sahudin, 2001). Therefore, branch-chained disulphide
polymers had received more attention due to less susceptible for degradation in low
pH condition of the stomach and more insoluble compared to linear-chained
disulphide polymers. Nevertheless, the insolubility feature of branch-chained
disulphide polymers would appear to be desirable in the stomach and small intestine
if the polymerisation of the polymers can be controlled. The important goal of the
polymer is to maintain the dosage form in an intact state and should be readily
degraded in low redox potential environment of the human colonic region.
Oxidative polymerisation method can be used for synthesis of disulphide cross-
linked polymer where the monomer is placed in a mild basic condition, exposed to
open air and with the presence of oxidising agent such as dimethyl sulphoxide
(DMSO) (Tan et al. 1991). DMSO is miscible with water at all concentrations, thus
it helps to improve the solubility of thiol monomers in aqueous solution. The
reaction mechanism of oxidation by DMSO was shown in Figure 1.6.