Subscriber access provided by UNIVERSITY OF TOLEDO LIBRARIES
Interfaces: Adsorption, Reactions, Films, Forces, Measurement Techniques, Charge Transfer, Electrochemistry, Electrocatalysis, Energy Production and Storage
Soft hydrogel zwitterionic coatings minimize fibroblast and macrophage adhesion on polyimide substrates Dusana Trelova, Alice Rita Salgarella, Leonardo Ricotti, Guido Giudetti, Annarita Cutrone, Petra Sramkova, Anna Zahoranova, Dusan Chorvat, Daniel Hasko, Claudio Canale, Silvestro Micera, Juraj Kronek, Arianna Menciassi, and Igor Lacik Langmuir, Just Accepted Manuscript • DOI: 10.1021/acs.langmuir.8b00765 • Publication Date (Web): 24 May 2018 Downloaded from http://pubs.acs.org on May 24, 2018
Just Accepted “Just Accepted” manuscripts have been peer-reviewed and accepted for publication. They are posted online prior to technical editing, formatting for publication and author proofing. The American Chemical Society provides “Just Accepted” as a service to the research community to expedite the dissemination of scientific material as soon as possible after acceptance. “Just Accepted” manuscripts appear in full in PDF format accompanied by an HTML abstract. “Just Accepted” manuscripts have been fully peer reviewed, but should not be considered the official version of record. They are citable by the Digital Object Identifier (DOI®). “Just Accepted” is an optional service offered to authors. Therefore, the “Just Accepted” Web site may not include all articles that will be published in the journal. After a manuscript is technically edited and formatted, it will be removed from the “Just Accepted” Web site and published as an ASAP article. Note that technical editing may introduce minor changes to the manuscript text and/or graphics which could affect content, and all legal disclaimers and ethical guidelines that apply to the journal pertain. ACS cannot be held responsible for errors or consequences arising from the use of information contained in these “Just Accepted” manuscripts.
is published by the American Chemical Society. 1155 Sixteenth Street N.W., Washington, DC 20036 Published by American Chemical Society. Copyright © American Chemical Society. However, no copyright claim is made to original U.S. Government works, or works produced by employees of any Commonwealth realm Crown government in the course of their duties.
Page 1 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
1
Soft hydrogel zwitterionic coatings minimize fibroblast and macrophage
2
adhesion on polyimide substrates
3 4
Dušana Treľová,a,# Alice Rita Salgarella,b,# Leonardo Ricotti,b,§ Guido Giudetti,b,§ Annarita
5
Cutrone,b,c Petra Šrámková,a Anna Zahoranová,a Dušan Chorvát Jr.,d Daniel Haško,d Claudio
6
Canale,e,f Silvestro Micera,b,g,* Juraj Kronek,a,*Arianna Menciassi,b,* Igor Lacíka,*
7 8 9 10 11
12
13
14
a
Department for Biomaterials Research, Polymer Institute of the Slovak Academy of Sciences,
Dúbravská cesta 9, 845 41 Bratislava, Slovakia b
The BioRobotics Institute, Scuola Superiore Sant’Anna, Viale R. Piaggio 34, 56025
Pontedera (PI), Italy c
SMANIA srl, via G. Volpe 12, 56121 Pisa, Italy
d
e
International Laser Centre, Ilkovičova 3, Bratislava 841 04, Slovak Republic
Department of Physics, University of Genova, Via dodecaneso 33, 16133 Genova, Italy
15
f
16
Genova (Italy)
17
g
18
and Institute of Bioengineering, Ecole Polytechnique Federale de Lausanne, Lausanne, CH
19
#,§
equally contributing authors
20
*
corresponding authors:
[email protected],
[email protected],
21
Department of Nanophysics, Istituto Italiano di Tecnologia (IIT), Via Morego 30, 16163
Bertarelli Foundation Chair in Translational Neuroengineering, Center for Neuroprosthetics
[email protected],
[email protected] 22
1 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
23
Abstract
24
Minimizing the foreign body reaction to polyimide-based implanted devices has a pivotal role
25
for several biomedical applications. In this work we propose materials exhibiting non-
26
biofouling properties and a Young's modulus reflecting the one of soft human tissues. We
27
describe the synthesis, characterization and in vitro validation of poly(carboxybetaine)
28
hydrogel coatings covalently attached to polyimide substrates via a photolabile 4-azidophenyl
29
group, incorporated in poly(carboxybetaine) chains at two concentrations of 1.6 and 3.1
30
mol.%. The presence of coatings was confirmed by attenuated total reflectance Fourier-
31
transform infrared spectroscopy. White light interferometry was used to evaluate coating
32
continuity and thickness (resulting between 3 and 6 µm in dry conditions). Confocal laser
33
scanning microscopy allowed to quantify the thickness of the swollen hydrogel coatings that
34
ranged between 13 and 32 µm. The different hydrogel formulations resulted in stiffness
35
values ranging from 2 to 19 kPa, and led to different fibroblasts and macrophages responses,
36
in vitro. Both cell types showed a minimum adhesion on the softest hydrogel type. In
37
addition, both the overall macrophage activation and cytotoxicity were observed to be
38
negligible for all the tested material formulations. These results are a promising starting point
39
towards future advanced implantable systems. In particular, such technology paves the way to
40
novel neural interfaces able to minimize the fibrotic reaction, once implanted in vivo, and to
41
maximize their long-term stability and functionality.
42
Keywords:
43
soft hydrogel coatings, poly(carboxybetaine), 4-azidophenyl, non-biofouling materials,
44
macrophage adhesion, fibroblast adhesion, polyimide, neural interfaces.
2 ACS Paragon Plus Environment
Page 2 of 44
Page 3 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
45
INTRODUCTION
46 47
Implantable devices are gaining an increasing relevance in the biomedical engineering field.
48
This is due to their high potential to restore the body functions after impairments and,
49
generally, to improve the patients’ quality of life.1 To address these clinical goals, it is
50
desirable to achieve a long-term functionality of implanted systems keeping them stable
51
within the body environment and avoiding undesired biological processes.
52 53
The implant long-term functionality is particularly important in the case of neural interfaces.
54
These systems are active implanted medical devices aimed at restoring a connection with the
55
central and peripheral nervous system after pathological conditions, such as neuropathies,
56
multiple sclerosis, amyotrophic lateral sclerosis or spinal cord injuries and limb amputations.2-
57
3
Exciting results have been recently achieved, which demonstrated the potential of this
58
implantable technology.4-6 Among the different options, polyimide (PI) has been identified as
59
a promising candidate material for the development of advanced neural interfaces. Indeed, it
60
is a biocompatible and flexible polymer featured by proper dielectric properties, thermal
61
stability, resistance to solvents and strong adhesion to metals and metal oxides. Moreover, it
62
can be easily patterned with lithographic and dry etching techniques and produced in the form
63
of thin layers by spinning deposition.7-9 Different PI-based interface designs have been
64
developed in the last years for selectively interfacing with the central nervous system for
65
intracortical neural activity recordings,10-11 cortical surface field potential recordings12 as well
66
as for intraneural interfacing with peripheral nerves.13-16
67 68
Currently, a full medical and commercial exploitation of neural interfaces is hampered by a
69
limited long-term implant stability. Intraneural implants are highly demanding since they
3 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
70
provide an intimate contact with axons, and trigger foreign body response and molecular
71
cascades related to chronic inflammation. This leads to the formation of a scar-like fibrotic
72
tissue that engulfs and electrically insulates the neural interface, thus altering the recording of
73
nerve action potentials and stimulation thresholds.3, 14, 17 This process starts already with the
74
injury produced by the invasive implantation procedure, which results in an acute
75
inflammation and leucocytes accumulation at the site of injury. Afterwards, the inflammation
76
becomes chronic, granulation tissue is produced by fibroblasts, and the foreign body reaction
77
proceeds with the accumulation of giant cells and fibrosis.18-19
78 79
Several strategies have been proposed to overcome the foreign body and inflammatory
80
reactions stimulated by implanted neural electrodes. In some cases the material surface was
81
functionalized with the aim of improving tissue integration within the implant. To this
82
purpose, adhesion molecules,20 specific peptides,21-23 and whole engineered proteins24 have
83
been proposed. Another strategy was based on the physical modification of the implant
84
surface, e.g. by providing it with proper patterns.25-27 A further option was to suppress adverse
85
local reactions by means of polymeric coatings exhibiting advanced features, such as
86
controlled release of bioactive molecules and/or non-biofouling surface properties.28-31 The
87
undesired host response to implants is due not only to their surface chemical properties, but it
88
is also determined by the mechanical mismatch between the implant and the surrounding
89
tissue.7, 32-33 The use of PI-based interfaces reduces this mismatch compared to silicon- and
90
glass-based interfaces. Nevertheless, the PI Young's modulus of a few GPa is significantly
91
higher than the Young's modulus of neural tissue, which ranges between 0.1 and 10 kPa.34
92
Moreover, it is known that the substrate stiffness influences the behavior of a wide variety of
93
cells, including macrophages, which are directly and primarily involved in the body reaction
94
to implants. Indeed, Blakney et al. demonstrated that macrophage activation is reduced on
4 ACS Paragon Plus Environment
Page 4 of 44
Page 5 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
95
softer poly(ethylene glycol)-based hydrogels exhibiting the elastic modulus in the range from
96
130 to 840 kPa.35 Softer hydrogels also induced a lower expression level of genes involved in
97
the production of inflammatory cytokines and showed a less severe foreign body reaction in
98
vivo. Hydrogel-based coatings can thus be considered a promising solution to minimize the
99
mechanical mismatch between implanted devices and tissues. These hydrogel coatings can be
100
produced in a wide range of Young's moduli (even a few kPa)36 and made of polymers
101
exhibiting non-biofouling properties.
102 103
Most of the polymeric layers proposed so far as neural interface coatings were based on
104
poly(ethylene glycol) (PEG) and PEG-based copolymers utilizing the PEG non-biofouling
105
properties.29-30,
106
Spencer et al. recently reported PEG-based hydrogels with controllable elastic moduli as
107
scarring-reducing coatings on neural probes.39 However, PEG is known to produce undesired
108
effects in vivo, e.g. oxidative damage in biological fluids, bioaccumulation in cell lysosomes
109
and generation of anti-PEG antibodies that may lead to a severe immune response.40-42
110
Therefore, the exploration of other types of non-biofouling polymers for a functional
111
protective coating of neural electrodes represents an ongoing challenge.
37-38
However, the role of stiffness was not investigated in these studies.
112 113
Zwitterionic
polymers,
including
poly(carboxybetaines),
114
poly(phosphobetaines), are non-toxic materials with a high hemocompatibility and ultralow
115
non-specific protein and cell adhesion.43-45 The mechanism behind this behavior was ascribed
116
to the formation of a hydration layer,46 which prevents hydrophobic interactions of proteins
117
and lipidic membranes of cells with the polymer surface. It was recently demonstrated that
118
surfaces decorated with zwitterionic molecules bind water molecules more strongly than PEG
119
due to electrostatically induced hydration.47 Strategies for surface attachment of zwitterion-
5 ACS Paragon Plus Environment
poly(sulfobetaines)
and
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Page 6 of 44
120
based compounds can be divided into “grafting from” and “grafting to” methods. In the first
121
case, methacrylates and methacrylamides containing zwitterionic moieties in a side chain are
122
polymerized via surface-initiated controlled radical polymerizations.48 The “grafting to”
123
method typically involves chemically induced attachment of zwitterionic polymers,
124
containing suitable chemical moieties, to the surface of other materials.49
125 126
Recently, zwitterionic polymers bearing photoactivated groups were used for the preparation
127
of covalently attached coatings via a photochemically controlled process. The overall benefits
128
of a photochemical surface modification are (i) formation of a stable bond with hydrocarbon
129
groups on various polymer substrates, (ii) simple manufacturing in dry state, and (iii)
130
possibility
131
phosphorylcholine and benzophenone units were used for modification of a commercial cyclic
132
polyolefine.50 Similarly, photoreactive poly(sulfobetaines) and poly(carboxybetaines) bearing
133
photolabile arylazide groups were applied for modification of various polymeric substrates.49,
134
51-53
of
micropatterning.
Photoreactive
copolymers
bearing
zwitterionic
However, to the best of our knowledge, zwitterionic polymers have never been
135
photochemically coupled with PI substrates in view of a future use in the domain of neural
136
interfaces.
137 138
In this paper, a zwitterionic hydrogel coating of PI substrates is proposed. The hydrogel is
139
based on poly(carboxybetaine methacrylamide) selected due to its favorable properties such
140
as biocompatibility, non-biofouling and hydration.54-55 The coating is obtained through a
141
photoactivated process enabled by a photolabile azidophenyl group. We aimed at exploiting
142
the non-biofouling properties of zwitterionic hydrogels and achieving low Young’s modulus
143
values in the range of the neural tissue. The hydrogel layers were characterized to verify the
144
presence of hydrogel attached to the PI surface, hydrogel thickness and Young’s modulus. In
6 ACS Paragon Plus Environment
Page 7 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
145
vitro tests with fibroblasts and macrophages were carried out to evaluate the adhesion of these
146
cells on the hydrogel-modified PI surfaces and to correlate these results with hydrogel
147
stiffness. This work thus contributes to create a strategy for neural interface coating and
148
envisions future applications of these materials in vivo.
149 150
EXPERIMENTAL PART
151 152
Materials
153
N-[3-(dimethylamino)propyl]methacrylamide,
154
hydrochloride, methacryloyl chloride, 2,2’-azobis(2-methylpropionamidine) dihydrochloride
155
(AIBA), amberlite IRA 400 chloride, and Pluronic F-127 were purchased from Sigma Aldrich
156
(Steinheim, Germany) and used as received. Sodium hydroxide, sodium carbonate, and
157
dioxane were purchased from Lachema (Brno, Czech Republic). Acetone, ethanol, and
158
dichloromethane were purchased from CentralChem (Slovakia) and distilled prior to use.
ethyl
bromoacetate,
4-azidoaniline
159 160
Preparation of 2-{dimethyl[3-(2-methylprop-2-enamido)propyl]ammonio}acetate (M1)
161
Monomer M1 was prepared by adapting the procedure described by Abraham and Unsworth56
162
(Scheme S1). N-(3-(dimethylamino)propyl)methacrylamide (5 g, 29 mmol) was diluted in 20
163
mL of acetone. Then ethyl bromoacetate (3.1 mL, 28 mmol) was added dropwise into the
164
reaction mixture under an argon atmosphere. The reaction mixture was stirred overnight at
165
room temperature. The white precipitate was filtered off, washed with acetone and dried
166
under reduced pressure. The resulting white powder was dissolved in distilled water and
167
applied onto a column filled with basic ionic exchange resin (Amberlite IRA 400) activated
168
for 30 min with 1 M aq. NaOH. After ion exchange, the solvent was evaporated and the
7 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
169
product was dried under reduced pressure. The resulting product was obtained as a colorless
170
viscous compound with a yield of 7 g (~ 100%). For 1H NMR spectrum of M1, see Figure S1.
171
1
H NMR (400 MHz, D2O, δ, ppm): 1.79 (s, CH3-C=CH2, 3H), 1.88 (m, -CH2-, 2H), 3.07 (s,
172
(CH3)2-N+, 6H), 3.22 (t, NH-CH2-, 2H), 3.43-3.47 (m, -CH2-N+, 2H), 3.72 (s, N+-CH2-COO-,
173
2H), 5.33 (s, CH2=, 1H), 5.59 (s, CH2=, 1H).
174 175
Preparation of N-(4-azidophenyl)-2-methylprop-2-enamide (M2)
176
Monomer M2 was prepared according to the procedure described by Ito et al (Scheme S2).57
177
Azidoaniline hydrochloride (501 mg, 2.9 mmol) was dissolved in 60 mL distilled water
178
containing sodium carbonate (933 mg, 8.8 mmol), and cooled down to 4 °C by using an ice
179
bath. Then, methacryloyl chloride (492 µL, 5.0 mmol) in 10 mL of dioxane was added
180
dropwise and the reaction mixture was stirred for 3 h in dark. The obtained precipitate was
181
filtered off, washed with distilled water and dried under reduced pressure. The resulting
182
product was obtained as a grey powder with a yield of 0.64 g (~ 100%). For 1H NMR
183
spectrum of M2, see Figure S2.
184 185
1
H NMR (400 MHz, CDCl3, δ, ppm): 2.05 (s, 3H, CH3), 5.45 (s, 1H, =CH2), 5.77 (s, 1H,
=CH2), 6.97-6.99 (dd, 2H, NH-Ar-H), 7.53-7.56 (dd, 2H, N3-Ar-H).
186 187
Copolymerization of M1 and M2
188
For the preparation of copolymers, two feeding molar ratios of M1/M2 were selected, namely
189
97.8/2.2 (copolymer C1) and 96.6/3.4 (copolymer C2). C1 was prepared as follows: M1 (320
190
mg, 1.4 mmol) was first dissolved in 3 mL of water/ethanol mixture (1:1 v/v), then M2 (6.2
191
mg, 0.031 mmol) and AIBA (8.2 mg, 0.03 mmol) were added. Three freeze-pump-thaw
192
cycles were applied and the reaction flask was filled with argon. The reaction mixture was 8 ACS Paragon Plus Environment
Page 8 of 44
Page 9 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
193
stirred for 4 h at 60 °C in dark. After cooling down, the reaction mixture was dialyzed against
194
a water/ethanol mixture (1:1 v:v, 3x) and distilled water (2x) using a Spectra/Por® dialyzing
195
tubing (MWCO 3.5 kDa, Spectrum Laboratories, Inc., CA, USA). After freeze-drying, 195
196
mg (yield 60%) of white powder were obtained. C2 was prepared with a similar procedure in
197
a yield of 287 mg (yield 71%). The dialysis steps as well as all subsequent manipulation with
198
copolymers C1 and C2 in either powder or solution forms were performed in dark.
199 200
1
H NMR (400 MHz, D2O, δ, ppm): 3.76 (s, N+-CH2-COO-, 2H), 3.50 (m, -CH2-N+, 2H), 3.10
(m, (CH3)2N+ and NH-CH2-, 8H), 1.85 (s, -CH2-, 2H), 0.97-0.84 (m, CH3, 3H).
201
202
Preparation of polyimide covered silicon wafers and round glass coverslips
203
Two different types of PI plates were prepared on different substrates, namely (i) round glass
204
coverslips (diameter: 6 mm), and (ii) square silicon (Si) wafers (2 x 2 cm2). Si wafers are
205
typically used as substrate for the preparation of PI based neural interfaces, by lithographic
206
and dry etching techniques, while for in vitro experiments glass coverslips were identified as a
207
more appropriate solution, so not to provide undesired biological response and to have rather
208
transparent substrates. Anyhow, on both substrate types a uniform PI layer was achieved. For
209
(i), a layer of PI resin (PI2610, HD Microsystems, Germany) was spun at 10,000 rpm for 30 s
210
onto the polished glass coverslips. Samples were then cured at 130 °C for 120 s and
211
subsequently hard baked in oven with nitrogen flux at 350 °C for 1 h (Carbolite, UK). Finally,
212
PI samples were washed twice with a liquid detergent (RBS 35 Concentrate, Belgium) in
213
order to eliminate contaminants and dust. For (ii), Si wafers (Si-Mat, Germany) were cut into
214
square samples (2 x 2 cm2) by using a diamond tip. Samples were cleaned in acetone for 10
215
min, rinsed with deionized water, cleaned with isopropanol for 10 min, and dried. Two layers
216
of PI resin were subsequently spin-coated at 2,000 rpm for 30 s. Samples were cured at 130
217
°C for 120 s and hard baked in oven with nitrogen flux at 350 °C for 1 h. 9 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
218
219 220
Deposition of copolymers C1 and C2 onto polyimide plates
221
Both types of PI plates were coated with the C1 and C2 copolymers. PI plates were first
222
washed in distilled water (3 min), ethanol (3 min), and dichloromethane (10 min) and
223
subsequently dried at room temperature and atmospheric pressure. Dry plates were then
224
uniformly covered with an aqueous solution of Pluronic F-127 with a concentration of 0.1 and
225
0.5 wt. %, respectively, using the solution volumes of 20 µL, in the case of (i) plates, and 283
226
µL, in the case of (ii) plates. Plates were dried overnight at room temperature and atmospheric
227
pressure. Aqueous solutions of C1 and C2 with a concentration of 0.5 and 1.0 wt. %,
228
respectively, were subsequently pipetted and homogeneously spread on the plate surface (20
229
µL in the case of (i) plates and 283 µL in the case of (ii) plates) to create a uniform layer of a
230
copolymer solution. Plates were dried overnight at room temperature and atmospheric
231
pressure in dark. Then they were irradiated by UV light for 20 min (UV Black Ray B100-A,
232
100 Watt, 365 nm, distance 5 cm) with a light intensity of 20-24 mW/cm2. These irradiation
233
conditions resulted from screening experiments that provided hydrogel layers permanently
234
attached to the the PI surfaces (Table S1). After irradiation, the samples were washed in
235
distilled water for 5 min and dried overnight at room temperature and atmospheric pressure
236
prior to characterization. The procedure used for formation of zwitterionic hydrogel layers
237
attached to PI surfaces is illustrated in Figure 1. The long-term storage conditions were room
238
temperature and protection from dust and light.
239 240
We selected the combinations of two copolymer types differing in the content of 4-
241
azidophenyl group, two different copolymer concentrations and two different surfactant
242
concentrations, which all were expected to affect the thickness and mechanical properties of 10 ACS Paragon Plus Environment
Page 10 of 44
Page 11 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
243
resulting hydrogel layers. In summary, six different protocols for fabricating polyzwitterionic
244
hydrogel layers covalently attached to the PI plates were selected using the experimental
245
conditions listed in Table 1. The hydrogel layers formed at the surface of PI plates were
246
characterized by attenuated total reflectance Fourier-transform infrared spectroscopy, white
247
light interferometry, confocal laser scanning microscopy, water contact angle measurements,
248
and nanoindentation (details given below).
249
250 251 252 253 254
Figure 1. Procedure for covalent modification of PI plates by zwitterionic hydrogel layer: (1) cleaning (in distilled water for 3 min, in ethanol for 3 min, and in dichloromethane for 10 min); (2) deposition of the surfactant solution; (3) deposition of the copolymer solution; (4) irradiation step, (5) cleaning (in distilled water for 5 min), and (6) characterization.
255 256
Nuclear magnetic resonance spectroscopy
257
Nuclear magnetic resonance spectroscopy (NMR) measurements were used to characterize
258
the structure of monomers and copolymers. 1H NMR spectra were measured at room
259
temperature in deuterated solvents (D2O, CDCl3) using a Varian 400-MR spectrometer
260
(Varian, USA) and tetramethylsilane (TMS) as an internal standard. 11 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
261 262
12 ACS Paragon Plus Environment
Page 12 of 44
Page 13 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
263
Attenuated total reflectance Fourier-transform infrared spectroscopy
264
Attenuated total reflectance Fourier-transform infrared spectroscopy (ATR-FTIR) spectra of
265
monomers, copolymers and hydrogel layers deposited on (ii) were measured by means of a
266
Nicolet 8700 FT-IR spectrometer (Thermo Scientific, USA) equipped with a Nicolet
267
Continuum Microscope and a germanium ATR crystal. Spectra were collected with a
268
resolution of 4 cm-1 using 128 scans. A software Omnic 8 (Thermo Scientific, USA) was used
269
for spectra evaluation.
270 271
UV/Vis absorbance spectroscopy
272
UV/Vis absorbance spectroscopy was used to determine the amount of M2 (N-(4-
273
azidophenyl)-2-methylprop-2-enamide) in C1 and C2 copolymers using a Shimadzu 1650 PC
274
spectrometer (Kyoto, Japan). A calibration curve was prepared from UV/Vis data for
275
monomer M2 dissolved in distilled water at the concentrations ranging from 0.01563 to
276
0.00125 g.L-1 (6.2 x 10-6 to 7.7 x 10-5 mol.L-1) and plotting the absorbance maxima at 273 nm
277
against concentration (Figure S3). Then the absorption spectra of C1 and C2 copolymers in 1
278
g.L-1 aqueous solutions were measured and molar content of M2 (cM2) in copolymers was
279
calculated from equation (1):
ಾమ
ಲమళయ
280
ܿெଶ (mol %) =
281
where A273 is the absorbance at 273 nm, MM1 and MM2 are the molar masses of the
282
corresponding monomers (MM1 = 228.29 g.mol-1, MM2 = 202.21 g.mol-1), nM1 and nM2 are the
283
molar fractions of monomers and ε is the extinction coefficient of monomer M2 (equivalent
284
to 4-azidophenyl group), equal to 10 680 L.mol-1.cm-1.
ಾమ ା ಾభ
*100 =
ε ಲమళయ ಲమళయ భష ε ∗ಾಾమ ା ಾಾభ ε
*100
285
13 ACS Paragon Plus Environment
(1)
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
286
Water contact angle
287
The hydrogel water contact angle was measured using the sessile drop technique with a
288
Surface Energy Evaluation system (SEE system with CCD camera, Advex Instruments,
289
Czech Republic). Dried hydrogel surfaces were wetted with a 3 µL water drop. For each
290
sample, 6 independent measurements were performed.
291
292
White light interferometry
293
Topography, surface roughness and thickness of hydrogel layers deposited on (ii) in their dry
294
state were assessed by a white light interferometry (WLI). A GT-K1 interferometer (Bruker,
295
USA) in vertical scanning interferometry mode, using a broad-band white light source, was
296
employed. Data were acquired and evaluated using a dedicated control and analysis software
297
package Vision 64. The topography was analyzed at the sample center, in order to capture the
298
topography of a continuous hydrogel layer, and at the edge, in order to capture the topography
299
of the layer and the PI substrate simultaneously. The surface area of approximately 4.5 x 3.5
300
µm2 was assessed for seven different positions of each hydrogel. A dry hydrogel layer
301
thickness was determined from controllably scratched layers in a swollen state (in distilled
302
water) using a scalpel to remove hydrogel and uncover the PI substrate. Subsequently, the
303
samples were washed with distilled water and dried for 24 h at room temperature and
304
atmospheric pressure prior to the WLI analysis. The reported thickness values represent the
305
average of six independent measurements made for each hydrogel type.
306 307
Confocal laser scanning microscopy
308
Confocal laser scanning microscopy (CLSM) in reflection and fluorescence modes was used
309
to determine the thickness of hydrogels deposited on (ii) in a swollen state. A LSM 510
310
META scanning confocal microscope head on Axiovert 200M inverted microscope (Zeiss, 14 ACS Paragon Plus Environment
Page 14 of 44
Page 15 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
311
Germany) was used with a 488 nm line of Ar:ion laser for sample excitation. Fluorescence
312
emission was detected through a 500-550 nm bandpass emission filter, the reflected laser light
313
was detected through a 435-485 nm bandpass filter and both channels were featured by a
314
pinhole setting of 1 Airy unit. Samples for CLSM measurements were prepared by careful
315
peeling off the PI layer with deposited hydrogel coating from the wafer surface. These
316
samples were placed between two microscopic coverslips separated by a glass spacer, made
317
of the coverslip, and stained with 0.5 mg/mL solution of IgG labelled with Alexa488
318
(ThermoFisher Scientific, USA) in PBS for 10 min prior to a measurement. All measurements
319
were done at room temperature. Images were obtained by scanning in the XZ plane with a 16x
320
line-averaging protocol using either PlanApochromat 20x/0.75 or C-Apochromat 40x/1.2W
321
Corr objectives. At least 5 independent images were acquired, with a total number of 15
322
measured height values determined for each hydrogel type, and averaged.
323
324
Nanoindentation via atomic force microscopy
325
Atomic force microscopy (AFM) in force spectroscopy mode58-59 was carried out to determine
326
the Young's modulus of hydrogels deposited on (ii) by using a Nanowizard III (JPK
327
Instruments, Germany) set-up. A Si nitride cantilever (DNP, Bruker, USA) with a nominal
328
spring constant of 0.24 N/m was used. The tip shape was pyramidal and the nominal radius at
329
the tip apex was 20 nm. The actual spring constant of each cantilever was determined by
330
using the in situ thermal noise method.60 All measurements were performed in a liquid
331
environment (PBS, Sigma-Aldrich, USA) at room temperature. The maximum force applied
332
on the samples was 2 nN. The velocity of the piezo-scanner was maintained constant at 3
333
µm/s. Force curves were corrected for the cantilever bending61 to calculate the tip-sample
334
separation and to build force vs indentation (F-I) curves. The Young’s modulus of the sample
335
was calculated by fitting the corresponding F-I curves with the Bilodeau model for a 15 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Page 16 of 44
336
pyramidal indenter.62 A proper fitting of the F-I curves was performed by means of a
337
dedicated data processing software provided by JPK Instruments. Five independent samples
338
were analyzed for each hydrogel type and each sample was indented at least in 50 different
339
points, randomly selected over the entire surface area.
340
341
Cell cultures and in vitro characterization
342
In vitro evaluation protocols were performed on the most important cell types responding
343
cooperatively to implanted biomaterials, namely fibroblasts and macrophages, as reported in
344
the sub-sections below. A qualitative assessment was also performed on a neural model (SY-
345
SY5Y cell line, CRL-2266™, ATCC®, Manassas, Virginia, USA), placed in close proximity
346
to the substrates. For this test, SY-SY5Y cells were seeded at a density of 30,000 cell/cm2,
347
cultured for 24 h in a mixture 1:1 of Dulbecco’s Modified Eagle’s Medium and Nutrient
348
Mixture F-12 (DMEM/F-12, Gibco™-Thermo Fisher Scientific, Waltham, Massachusetts,
349
USA), supplemented with Fetal Bovine Serum (FBS, Gibco™-Thermo Fisher Scientific,
350
Waltham,
351
Penicillin/Streptomycin
352
Massachusetts, USA) to a final concentration of 1 %, and then imaged in bright field to check
353
their presence and shape.
Massachusetts,
USA)
to
(PEN/STREP,
a
final
concentration
Gibco™-Thermo
Fisher
of
10%,
Scientific,
and
with
Waltham,
354 355
Fibroblast culture, adhesion and cytotoxicity tests
356
Normal human dermal fibroblasts, nHDFs (Cat. # CC-2511, Lonza, Basel, Switzerland) were
357
cultured using a complete growth medium composed of high-glucose Dulbecco’s Modified
358
Eagle’s Medium (DMEM, Gibco™ - Thermo Fisher Scientific, Waltham, Massachusetts,
16 ACS Paragon Plus Environment
Page 17 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
359
USA) with phenol-red supplemented with FBS to a final concentration of 10%, and with
360
PEN/STREP to a final concentration of 1 %.
361
For adhesion tests, round glass coverslips (6 mm diameter) covered with PI (i) (control
362
samples) and with PI further coated with selected zwitterionic hydrogels were used. Briefly,
363
the samples were placed in 48-well plates, washed once with PBS and then incubated for 1 h
364
in PBS, in order to let hydrogels swell. Then, samples were washed again with PBS
365
supplemented with PEN/STREP (1 %) and conditioned with the complete growth medium for
366
5 h. nHDFs were then seeded on the samples at a density of 15,000 cells/cm2 and cultured for
367
24 h. To evaluate cell adhesion on the different substrates, cells were stained for nuclei with
368
Hoechst 33342 (Molecular Probes™-Thermo Fisher Scientific, Waltham, Massachusetts,
369
USA). Hoechst 33342 was diluted to a final concentration of 10 µg/mL in Dulbecco's PBS
370
(DPBS, Gibco™-Thermo Fisher Scientific, Waltham, Massachusetts, USA), added to cells
371
and kept for 5 min at room temperature. Glass plates were then turned upside down to bypass
372
PI autofluorescence and imaged by means of a UV/Vis microscope (ECLIPSE Ti-E, Nikon
373
Corporation, Minato-ku, Tokyo, Japan). Images of the blue channel (stained nuclei, bandpass
374
filter value equal to 461 nm) were acquired at 10x magnification and the number of nuclei per
375
image was quantified through the ImageJ® software (National Institutes of Health, Bethesda,
376
Maryland, USA; available at https://imagej.nih.gov/ij/). Three independent plates were
377
analyzed for each sample type, including the control, to quantitatively evaluate cell adhesion.
378
Three images on different areas were acquired for each sample.
379
Whole cell morphology was also qualitatively assessed. To this purpose, at the same time-
380
point (24 h) cells were fixed with a paraformaldehyde (Sigma Aldrich® Corporation, St.
381
Louis, Missouri, USA) solution in PBS (4 % w/v) for 15 min, then permeabilized with 0.1 %
382
Triton X-100 (Sigma Aldrich® Corporation, St. Louis, Missouri, USA) in PBS for 15 min and
383
finally co-stained for 15 min for actin fibers with tetramethylrhodamine B isothiocyanate 17 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
384
labeled Phalloidin (Sigma Aldrich® Corporation, St. Louis, Missouri, USA) as well as for
385
nuclei with Hoechst (as described above). Fluorescence images (blue and red channels,
386
bandpass filter values equal to 461 and 570 nm) were acquired at 10x magnification.
387
For cytotoxicity tests, a Pierce LDH Cytotoxicity Assay kit (Thermo Fisher Scientific,
388
Waltham, Massachusetts, USA) was used. Lactate dehydrogenase (LDH) is a cytosolic
389
enzyme that is released in the cell culture medium after the cell plasma membrane is
390
damaged. LDH can be quantified spectrophotometrically by means of a coupled enzymatic
391
reaction that leads to the formation of red insoluble formazan, which is directly proportional
392
to the amount of LDH released. To perform this experiment, round glass coverslips (6 mm
393
diameter) covered with PI (i) (control samples) and with PI further coated with selected
394
zwitterionic hydrogels were placed into 96-well plates, pretreated with PBS and complete
395
growth medium as described above. nHDFs were then seeded at a density of 25,000 cells/cm2
396
(200 µL of cells suspension in complete growth medium, without phenol red that would
397
interfere with the measurements, per each well) both on covered round glass coverslips (3
398
coverslips per sample type) to assess substrate-induced LDH activity, and on tissue culture
399
polystyrene wells to assess spontaneous and maximum LDH activity (3 wells per type). Cells
400
were cultured for 24 h, then treated according to the LDH kit manufacturer’s instructions
401
properly adapted to the samples. Absorbance at 490 nm (related to LDH amount) was
402
measured (3 replicates for each sample) with a plate reader (Victor X3, Perkin Elmer,
403
Waltham, Massachusetts, USA). Background was removed and the cytotoxicity was
404
computed for each hydrogel and for PI as: % Cytotoxicity = (substrate-induced LDH activity -
405
spontaneous LDH activity) / (maximum LDH activity - spontaneous LDH activity).
406 407
Macrophage culture, adhesion and activation tests
18 ACS Paragon Plus Environment
Page 18 of 44
Page 19 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
408
The murine RAW 264.7 macrophage cell line (ATCC® TIB-71™, ATCC®, Manassas,
409
Virginia, USA) was cultured in the same complete growth medium used for nHDFs.
410
For adhesion tests, round glass coverslips covered with PI (i) (control samples) and with PI
411
coated with selected zwitterionic hydrogels were placed in 48-well plates and pretreated
412
similarly to fibroblasts (see above). RAW 264.7 cells were then seeded at a density of 30,000
413
cells/cm2 and cultured for 24 h. The cell nuclei were stained with Hoechst 33342 and imaged,
414
similarly to nHDFs. Three independent plates were analyzed for each sample type, including
415
the control, and three images were acquired for each sample on different areas.
416
Similarly
417
tetramethylrhodamine B isothiocyanate labeled Phalloidin and Hoechst. In order to compare
418
macrophage morphology changes due to activation, the same cell density was seeded on
419
tissue culture polystyrene wells and left to attach for 4 h. Then, lipopolysaccharide (LPS)
420
from Escherichia coli 055:B5 (Sigma Aldrich® Corporation, St. Louis, Missouri, USA) was
421
added to a concentration of 1 µg/mL and incubated for 24 h, to provide a positive control for
422
activation. Then, cells underwent fixation, permeabilization and staining as described above.
423
Macrophage activation was evaluated through the assessment of nitric oxide production.
424
Nitrite (NO2-), a stable breakdown product of NO, was measured by means of a Griess
425
Reagent system (Promega Corporation, Madison, Wisconsin, USA). Round glass coverslips
426
(6 mm diameter) covered with PI (i) (control samples) and with PI further coated with
427
selected zwitterionic hydrogels were placed in 96-well plates and pretreated as described
428
above. RAW 264.7 were seeded at a density of 80,000 cells/cm2 (150 µL of cells suspension
429
in a complete growth medium without phenol red per each well) both on samples and on bare
430
tissue culture polystyrene. The latter samples were used as negative and positive controls to
431
assess nitrite release from activated macrophages: the cells were cultured for 4 h, then 50 µL
to
nHDFs,
qualitative
cell
imaging
was
19 ACS Paragon Plus Environment
also
performed
through
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
432
of complete growth medium with/without LPS (1 µg/mL) was added to induce macrophage
433
activation, while all other PI samples were only provided with complete growth medium in
434
order to compensate for volume increase. Cells were exposed to the different substrates or to
435
LPS for 24 h, then the Griess assay was performed, according to the manufacturer’s
436
instructions. The absorbance at 560 nm for each sample was measured with a plate reader
437
(Victor X3, Perkin Elmer, Waltham, Massachusetts, USA). Three independent samples were
438
analyzed for each sample type and three absorbance reading replicates were measured for
439
each sample.
440
441
Data analyses
442
Data underwent a non-parametric statistical analysis using a Kruskal-Wallis post-hoc test and
443
a Dunn's multiple comparison test in order to evaluate significant differences among the
444
samples. Results were considered statistically different for p-values ≤ 0.05.
445 446
RESULTS AND DISCUSSION
447
Preparation and photoimmobilization of zwitterionic copolymers
448
Two photoreactive zwitterionic copolymers C1 and C2, differing in the content of photolabile
449
4-azidophenyl groups, were prepared by the radical copolymerization of 2-{dimethyl[3-(2-
450
methylprop-2-enamido)propyl]ammonio}acetate (M1) with N-(4-azidophenyl)-2-methylprop-
451
2-enamide (M2) bearing photoreactive 4-azidophenyl unit (Figure 2). The chemical structure
452
of monomers and copolymers was determined by NMR and ATR-FTIR spectroscopies. The
453
presence of small broad signals in the range from 7 to 7.5 ppm in 1H NMR spectrum revealed
454
the presence of 4-azidophenyl group in the structure of both copolymers (Figures S4 and S5). 20 ACS Paragon Plus Environment
Page 20 of 44
Page 21 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
455
In the ATR-FTIR spectra of C1 and C2, a small vibration band of the azide group was
456
observed at 2119 cm-1 (Figure S6). Asymmetric and symmetric stretching vibrations of
457
carboxylate group of zwitterionic unit were present at 1630 and 1380 cm-1. Vibration bands
458
connected to N-H bond of zwitterionic unit were also visible at 1529 and 1483 cm-1. All
459
signals were in accordance with results published recently by Sobolčiak et al.53
460 461 462
Figure 2. Scheme of the synthesis of zwitterionic copolymers C1 and C2 containing photolabile 4-azidophenyl groups.
463
464
Molar percentages of 4-azidophenyl groups in copolymers C1 and C2 of 1.6 and 3.1 mol.%,
465
respectively, were calculated from UV/Vis absorbance spectra of copolymers in water using
466
the calibration curve for M2 (Figure S3) and equation (1). These values were slightly lower
467
compared to feeding M2 comonomer content equal to 2.2 and 3.4 mol.% for C1 and C2,
468
respectively, probably due to an incomplete conversion and a minor compositional drift in
469
favor to consumption of M1 comonomer.
470
471
Characterization of PI plates modified by polyzwitterionic layers
21 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Page 22 of 44
472
The aim of this study was to identify the conditions for a covalent attachment of soft
473
zwitterionic hydrogel layers (with a thickness in the micrometer range) to the PI surface. In
474
order to achieve this goal, we adapted principles that employ a photoactivated attachment of
475
zwitterionic polymers via a C-H insertion reaction using 4-azidophenyl groups,49,
476
schematically shown in Figure 3.
53
477 478 479 480 481 482 483 484 485 486 487 488 489 490 491
Figure 3. Schematic representation of crosslinking and grafting process of zwitterionic copolymers C1 and C2 by C-H insertion of nitrene, created from a photolabile 4-azidophenyl groups during UV-light irradiation (365 nm), with the hydrocarbon units of either zwitterionic copolymer or polyimide surface.
492 493
The experimental conditions used for hydrogel fabrication, such as distance between the UV
494
lamp and the surface, irradiation time, copolymer and surfactant concentrations, were
495
optimized to obtain hydrogel layers stably bound to the surface (Table S1). Based on these
496
data, we selected the irradiation conditions, which were kept constant for all experiments.
497
Although the studied parameters are mutually interrelated, we could conclude that the stability
498
of attached layers decreases with increased copolymer concentration (≥ 3 wt.%) and longer 22 ACS Paragon Plus Environment
Page 23 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
499
lamp distance (> 5 cm). Similar observations were reported by Roger et al.,63 where the
500
authors observed decreasing of grafting yield with increased either concentration or volume of
501
carbohydrate bearing 4-azidophenyl group. This was explained by lower penetration depth of
502
UV light leading to ineffective grafting in case of thicker layers.
503 504 505 506 507
Table 1. Preparation conditions and properties of zwitterionic hydrogel coatings covalently attached to PI substrates. Water contact angles, dry (hdry) and wet (hwet) thickness, surface roughness (Ra) in a dry state, and Young’s moduli are expressed as the mean value ± standard deviation.
Sample
M2 in Copolymer Pluronic Contact copolymer F-127 angle a) [wt.%] [wt.%] [°] [mol.%]
[µm]
[µm]
[µm]
Young’s moduluse) [kPa]
59 ± 3
5.1 ± 0.3
0.16 ± 0.06
13 ± 2
2.7 ± 0.2
1.0
0.5
66 ± 9
6.4 ± 0.4
0.10 ± 0.03
32 ± 5
2.0 ± 0.2
0.5
0.1
33 ± 6
4.6 ± 0.6
0.13 ± 0.05
28 ± 6
12 ± 3
H4
1.0
0.1
45 ± 4
5.2 ± 0.2
0.30 ± 0.10
24 ± 6
15 ± 2
H5
0.5
0.5
34 ± 6
4.8 ± 0.9
0.14 ± 0.02
14 ± 3
5.2 ± 0.8
H6
1.0
0.5
39 ±4
3.1 ± 0.4
0.12 ± 0.05
24 ± 4
19 ± 4
H3
511 512 513 514 515 516
hwetd)
0.1
H2
508 509 510
Rab)
1.0
H1
1.6
hdryb,c)
3.1
a)
the measured water contact angle for PI plate was 75° determined by white light interferometry for dried hydrogels c) hdry theoretical values are 3.5 and 7.0 µm for coatings using 0.5 and 1.0 wt.% of copolymer, respectively, assuming Pluronic F-127 does not take part in the layer formation and the copolymer density is 1 g.cm-3 d) determined by confocal laser scanning microscopy for wet hydrogels in PBS e) determined by AFM nanoindentation for wet hydrogels in PBS b)
517
The characterization of polyzwitterionic hydrogel layers on PI substrates included surface
518
chemical analysis and measurement of wettability, thickness, surface roughness and
519
mechanical properties. These data are summarized in Table 1, together with the conditions
520
used for fabricating the six representative hydrogel types (H1 - H6).
521
23 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
522
The modification of PI substrates by hydrogel layers was characterized by ATR-FTIR, shown
523
in Figure 4, using non-modified PI substrate and C1 and C2 copolymers as controls. In
524
agreement with previously published data,64 the spectrum of non-modified PI consists of
525
peaks, which can be assigned to the asymmetric stretching vibration of C=O group at 1773
526
cm-1, the symmetric stretching vibration of C=O group at 1708 cm-1, C-N stretching vibration
527
at 1352 cm-1 and imide five-ring deformation vibration at 734 cm-1 (Figure S7a). The PI and
528
copolymer vibration peaks in the ATR-FTIR spectra of hydrogel layer-coated PI plates were
529
present at different intensities depending on the sample type (Figure 4). The layers prepared
530
of lower 0.5 wt.% copolymer concentration (H3 and H5, Figure 4b) showed a significant
531
presence of PI vibrations in the spectra compared to the layers prepared of 1.0 wt.%
532
copolymer concentration. This observation was surprising as it did not correlate with the WLI
533
analysis showing, in Figure 5, a complete coverage of PI plates, the thickness, hdry, in the
534
range from 3 to 6 µm (Table 1), and considering the penetration depth of the infrared beam
535
approximately 1 µm for Ge crystal.65 Figure 5 shows the WLI images for hydrogel layers in
536
their centers, verifying a complete PI surface coverage and a high degree of layer smoothness,
537
which was quantitatively expressed by the surface roughness values, Ra, ranged from 0.1 to
538
0.3 µm (Table 1). Figure 5 also reveals the images of the plate edges to visualize the situation
539
for imperfect PI surface coverage that is in contrast to complete coverage of the sample
540
central areas. The Ra values resulted less than 10 % of the thickness values for the dry layers,
541
determined as the height difference between the surface of hydrogel and the PI surface
542
obtained after careful removal of the hydrogel layers by a scalpel, in a swollen state (Figure
543
S8). Overall, the ATR-FTIR and WLI data show that the PI vibration peaks in the ATR-FTIR
544
spectra shown in Figure 4 could not result from a non-coated PI surface or from the extensive
545
surface roughness. We propose that the presence of the PI in the FTIR spectra was rather due
546
to using ATR mode for these very soft hydrogel layers, featured by a thickness of a few
24 ACS Paragon Plus Environment
Page 24 of 44
Page 25 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
547
micrometers. During the analysis, the hydrogel layers were likely compressed by the ATR
548
crystal towards the hard substrate (PI on silicon wafer, (ii)) resulting in the analytical
549
thickness that was within the infrared beam penetration depth.
550 551
The ATR-FTIR spectra for all hydrogel layers in Figure 4 highlighted also the position of the
552
high intensity C-O stretching vibration at 1102 cm-1 for Pluronic F-127 (the individual ATR-
553
FTIR spectra for Pluronic F-127 are shown in Figure S7b). Pluronic F-127 was used as a
554
surfactant during the hydrogel fabrication, for wetting the PI hydrophobic surface prior to
555
deposition of the copolymer solution. Its presence in the hydrogel layer was assumed since
556
the C-H insertion reaction may proceed also with the alkyleneoxy units of Pluronic F-127
557
molecule. The Pluronic F-127 concentration is in the range of copolymer concentration (0.1
558
and 0.5 wt.%, Table 1); therefore, its high intensity vibration at around 1100 cm-1 was
559
expected to be detected. However, this was not the case (Figure 4) and it is not trivial to
560
understand whether this behavior corresponds with a negligible incorporation of this
561
surfactant into the hydrogel layer followed by its gradual washing from the hydrogel, or with
562
the overlap of PI and Pluronic F-127 bands in this region of FTIR spectra.
563
564
The hydrogel layer deposited on PI substrates modified the surface wettability. The contact
565
angle determined for a non-modified PI plate was 75°, a value close to the one reported in the
566
literature (72°).66 The coating of PI plates by zwitterionic hydrogels reduced this contact angle
567
to values included in the range between 33° and 66°, as reported in Table 1. These values are
568
in the same range as previously reported for other zwitterionic polymer layers, with a
569
thickness typically in the sub-micrometer range.49,
570
hence, a slightly more hydrophobic surface, was observed for layers formed from C1
571
copolymer of lower 4-azidophenyl content compared to the layers based on C2 copolymer,
52-53, 66-68
25 ACS Paragon Plus Environment
A higher contact angle and,
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
572
especially at the lower C2 content of 0.5 wt.%. During the formation of these hydrogel layers,
573
two competing C-H
574
575 576 577 578 579
Figure 4. ATR-FTIR spectra of (a) H1 and H2 hydrogel layers compared to PI surface and copolymer C1 and (b) H3-H6 hydrogel layers compared to PI surface and copolymer C2, in a wavenumber region from 2200 to 600 cm-1. Dashed lines depict the characteristic bands for PI, copolymers and Pluronic F-127. 26 ACS Paragon Plus Environment
Page 26 of 44
Page 27 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
580
27 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
581 582 583 584
Figure 5. White light interferometry visualization of hydrogel coatings on a PI substrate in the sample center and edge, respectively, for selected samples H1-H2 (made of the copolymer C1), H3-H6 (made of the copolymer C2). The main preparation conditions of hydrogels are given in Table 1.
585
586
insertion reactions of nitrene radicals proceed concurrently, i.e., with the PI surface and within
587
the copolymer chains, resulting in the attachment of the hydrogel layer to the surface and the
588
intra- and intermolecular crosslinking of C1 resp. C2 copolymer chains, respectively (Figure
589
3). The competition between these two pathways was suggested to control the water contact
590
angle for poly(carboxybetaine) layers deposited by photoactuation to various polymer
591
substrates.53 In our case, the obtained water contact angle data provide no clear reason why
592
the hydrogels made of C1 copolymer would experience a higher intra- and intermolecular
593
crosslinking compared to hydrogels made of C2 copolymer with a slightly higher content of
594
4-azidophenyl group. This issue remains open also in view of the Young’s modulus data
595
(reported in Table 1 and discussed below), showing that the hydrogel layers based on C2
596
copolymer are stiffer than those based on C1 copolymer, under identical conditions.
597 598
Hydrogel thickness values in a swollen state, hwet, ranged between 13 and 32 µm (Table 1).
599
They were determined by a CLSM technique, as shown in Figure 6. This is an important
600
feature of the layers, for their future deposition on the surface of real neural electrodes. This
601
method enabled to precisely visualize the swollen layer as a dark object well-visible in the
602
PBS solution containing the IgG labeled with Alexa 488 (Figure 6a). The labeled IgG did not
603
significantly penetrate inside the hydrogel volume within the time-scale of CLSM analysis.
604
This arrangement eliminated the influence of strong fluorescence emission of the PI layer
605
compared to Alexa 488-labeled IgG (Figure 6b). The CLSM images of hydrogels H2, H5 and
606
H6 (i.e., the samples used for the in vitro experiments discussed further below) are shown in 28 ACS Paragon Plus Environment
Page 28 of 44
Page 29 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
607
Figure 6c. The hwet values did not correlate with either preparation conditions or hdry values.
608
In addition, the thickness of individual swollen hydrogels (Figure 6c) exhibited a significant
609
variation that was not expected from the low Ra values obtained for the dry layers (Table 1).
610
This suggests that the uneven swelling of hydrogel layers may be caused by a crosslinking
611
reaction that did not proceed homogeneously within the entire hydrogel volume irradiated in
612
the dry state.
613 614 615 616 617 618 619
Figure 6. Determination of the thickness of hydrogel layers swollen in PBS by CLSM. (a) Schematic illustration of experiment arrangement for CLSM measurement: 1. Glass coverslip, 2. Solution of Alexa 488-labeled IgG in PBS (c = 0.5 mg/mL), 3. PI layer, 4. Hydrogel layer, 5. Glass spacer, (b) comparison of fluorescence spectra of PI layer and solution of Alexa 488labeled IgG in PBS, and (c) CLSM images of H2, H5 and H6 in solution of Alexa 488-labeled IgG in PBS (scale bar is 20 µm).
620
621
The hydrogel Young’s moduli, determined in a PBS liquid environment by AFM
622
measurements (Figure S9) are reported in Table 1 and plotted in Figure 7. The layers made of
623
C1 copolymer with a lower 4-azidophenyl content exhibited Young’s modulus of around 2
624
kPa. A higher content of 4-azidophenyl groups in the C2 copolymer resulted in a Young’s
625
modulus increase up to 20 kPa depending on the copolymer concentration. Young’s modulus 29 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
626
data do not correlate with the content of Pluronic F-127. Rather, they are associated with the
627
network density, which is in turn proportional to the 4-azidophenyl content and to the
628
polymer concentration. Note that the higher network density for C2 copolymer was not
629
demonstrated by the hwet with expected lower thickness in the swollen state than for C1
630
copolymer due to lower swelling. Neither the higher network density for C2 copolymer
631
resulted in a higher water contact angle compared to hydrogels made of C1 copolymer. Even
632
though some of the obtained data would require further understanding, the employed strategy
633
successfully served the primary aim of this study that was to covalently coat stiff PI plates by
634
zwitterionic hydrogels of low stiffness, thus approaching the stiffness of neural tissues.
635 636 637 638 639 640
Figure 7. Young’s moduli of zwitterionic hydrogels H1-H6 deposited on PI plates, and of the PI plate assessed by AFM nanoindenting in PBS. Box and whisker plots show the median values and interquartile ranges (whisker represent the maximum and minimum values obtained). **** = p < 0.0001.
30 ACS Paragon Plus Environment
Page 30 of 44
Page 31 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
641
642
In vitro experiments
643
In vitro tests were performed on three hydrogel types coated on the PI plates i): H2, H5 and
644
H6. These were selected based on their Young’s modulus and chemical composition. In
645
particular, we selected the hydrogels with the lowest and the highest Young’s modulus,
646
respectively, H2 and H6, which featured the same amount of copolymer and Pluronic F-127,
647
but different content of 4-azidophenyl groups. As a third sample type, we selected the H5
648
hydrogel, which showed an intermediate value of Young’s modulus and the same Pluronic F-
649
127 content as H2 and H6 samples (see Table 1).
650 651
Fibroblast adhesion and morphology were evaluated by fluorescence imaging of living and
652
fixed nHDF cells cultured on H2, H5 and H6 hydrogels and on PI controls. Figure 8a shows
653
the fluorescence patterns of actin (stained in red) and nuclei (stained in blue) in cells attached
654
on the different substrates. In particular, almost no adhesion was found on H2 samples, while
655
cells formed few clusters in scattered areas of the H5 and H6 samples. In contrast, cells on PI
656
samples were well spread on the entire sample surface and there was no cluster formation.
657
The cell density (in terms of) cells/cm2 was evaluated by counting the stained nuclei of living
658
nHDFs attached on the different substrates; the results are reported in Figure 8b. Overall, a
659
strong reduction of cell adhesion was observed for the samples covered with zwitterionic
660
hydrogels compared to PI samples (median value reduction: H2 = 97.4%, H5 = 79.4% and
661
H6 = 72.6 %). Comparing the fibroblast adhesion on the three different hydrogels, a statistical
662
difference was found between sample H2 and H5 (p = 0.0087) and between H2 and H6 (p =
663
0.0003), which suggests that the lowest Young’s modulus of H2 hydrogel reduces the cell
31 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
664
adhesion in a higher degree than for hydrogels H5 and H6 of somewhat higher Young’s
665
modulus.
666 667
The obtained results are in a good agreement with previously published data. Stach et al.
668
described significant reduction of RAT-2 fibroblasts adhesion on poly(sulfobetaine) modified
669
conductive surfaces using electrografting method.69 Significant reduction of RAT-2
670
fibroblasts adhesion was observed also in the case of zwitterionic hydrogels spin-coated on
671
glass coverslips.70 Similarly, the photoimmobilized sulfobetaine and carboxybetaine-based
672
polymeric films significantly inhibited the non-specific adhesion of fibroblast-like STO
673
mammalian cells in comparison with non-modified substrates.52 In the work of Chien et al.,
674
L929 cells well adhered on the non-modified poly(styrene) surface while cell adhesion was
675
inhibited almost completely on the poly(carboxybetaine)-modified surfaces.49 All these data,
676
including those obtained in this work, indicate that immobilization of either sulfo- or
677
carboxybetaine zwitterionic polymers on different surfaces enables to reduce cell adhesion in
678
a significant way. Concerning neural electrode coatings featured by tuned mechanical
679
properties, the sole recent study we can refer to is the work of Spencer et al.39 Here, the
680
authors demonstrated that PEG-based hydrogels with a Young’s modulus of ~ 10 kPa
681
significantly reduced the scarring process in vivo with respect to stiffer implants (glass
682
capillaries, with a Young’s modulus of ~ 70 kPa). The scarring process involves several
683
events, included the adhesion of fibroblasts on the implant surface. Thus, although with
684
several differences, i.e. in vitro vs in vivo data, different materials involved, different stiffness
685
values investigated, our results can be considered in line with what reported by Spencer et
686
al.39 It is worth mentioning that in our work we further clarified the role of stiffness in this
687
process, showing that values well below 10 kPa (almost one order of magnitude smaller)
688
prevent fibroblast adhesion more efficiently. 32 ACS Paragon Plus Environment
Page 32 of 44
Page 33 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
689
690
Cytotoxicity of the different substrates was evaluated using nHDFs fibroblasts by quantifying
691
the LDH release; results are reported in Figure 7c. Almost no cytotoxicity was observed for
692
all the samples (the highest median value was 0.7%, found for the H5 sample), in agreement
693
with previous studies performed with NIH-3T3 fibroblasts on zwitterionic hydrogels.71-72 No
694
statistical difference was found between the different hydrogels and the PI samples.
695 696 697 698 699 700 701 702 703
Figure 8. In vitro evaluation of zwitterionic hydrogels on fibroblast cells. (a) Fluorescence images at 10x magnification of nHDF cells on zwitterionic hydrogels H2, H5, H6 and on PI samples, showing nuclei stained in blue and actin in red (scale bar = 100 µm). (b) Quantification of the adhesion of nHDF fibroblasts on zwitterionic hydrogels and on PI samples after 24 h culture. The box and whisker plots represent the median values and interquartile ranges of the number of adherent cells per cm2 (whiskers represent the maximum and minimum values obtained). ** = p < 0.01, *** = p < 0.001. (c) Quantification of the 33 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
704 705 706 707 708
cytotoxicity percentage of zwitterionic hydrogels and PI by LDH cytotoxicity assay measured using nHDF fibroblasts after 24 h culture on substrates. The box and whisker plots represent the median values and interquartile ranges (whiskers represent the maximum and minimum values obtained).
709
As for fibroblasts, macrophages adhesion and morphology was evaluated by fluorescence
710
imaging of both living and fixed RAW 264.7 cells cultured on H2, H5 and H6 hydrogels and
711
on PI controls. Fluorescence images of actin (stained in red) and nuclei (stained in blue) of
712
cells attached on different substrates are shown in Figure 9a. Macrophages reflected the
713
fibroblasts behavior: almost no adhesion was observed on H2 samples and cells formed few
714
clusters in scattered areas of H5 and H6 samples, while well spread cells were found on the PI
715
samples, without cluster formation. A large reduction of cell adhesion was observed in the
716
samples covered with zwitterionic hydrogels with respect to PI samples (median value
717
reduction: H2 = 98.9%, H5 = 93.2% and H6 = 90.8 %), see Figure 9b. This cell behavior is in
718
agreement with the one observed in the study of Khandwekar et al., where sulfobetaine
719
molecules were entrapped on poly(methyl methacrylate) surfaces leading to a reduction of
720
RAW 264.7 cells adhesion.73 Comparing adhesion of macrophages on the three different
721
hydrogels, a statistical difference was found between sample H2 and H5 (p = 0.0247) and
722
between H2 and H6 (p = 0.0019). The lower adhesion of macrophages on H2 samples may be
723
again explained by its low Young's modulus value. In literature, a stiffness-based influence on
724
macrophages adhesion has been reported, although on another cell line, THP-1.74 Differently,
725
Blakney et al. indicated that substrate stiffness did not play a role in RAW 264.7 cell
726
attachment. However, in this case, the investigated Young’s moduli were in the range of
727
hundreds of kPa.35
728
729
Macrophages activation was evaluated by assessing nitric oxide (NO) production,75 in
730
particular by measurement of nitrite release in the supernatant. NO is a physiological 34 ACS Paragon Plus Environment
Page 34 of 44
Page 35 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
731
messenger and effector molecule involved in several biological processes. It is released in
732
excess during host response and it contributes to pathogenic conditions by promoting
733
oxidative stress. The nitrite concentrations are reported in Figure 9c, together with the values
734
of a positive and a negative controls for comparison, namely cells cultured on tissue culture
735
polystyrene and the same cells stimulated by LPS.76 There was no statistical difference
736
between the samples exhibiting very low absolute concentration for each hydrogel type (the
737
highest median value was found for H5 = 0.3 µM). These values were almost comparable
738
with the negative control of non-activated cell (except for samples H6 and PI for which a
739
lower reduction of nitrite production was found) and much lower than the amount of nitrite
740
released by LPS-activated macrophages used as a positive control for inflammation. This was
741
confirmed by morphological evaluation: on each sample, the cells that attached maintained a
742
round shape (Figure 98a), a morphology that is typical of non-activated cells (Figure 9d, top
743
image), whereas LPS-stimulated cells tend to spread on the surface and thus to increase their
744
adhesion area (Figure 9d, bottom image).
745
746
The four substrates were also incubated in the presence of a human bone marrow
747
neuroblastoma derived cell line, SY-S5Y5, so to qualitative prove their ability to safely
748
adhere without any abnormal morphological changes and keep a healthy shape in close
749
proximity to the coatings. Bright field images of cells 24 h after seeding are shown in Figure
750
S10 of Supporting Information. The hydrogels prevented the adhesion of neural cells,
751
similarly to fibroblasts and macrophages. However, the neural cells were able to adhere and
752
maintain the morphology and keep a healthy shape in close proximity at the interface between
753
hydrogel and glass surfacesto the hydrogels, comparably to the PI substrate. This further
754
confirmed the suitability of the coatings analyzed in this paper, in view of future in vivo
755
experiments. Neural interfaces, in fact, will be inserted into peripheral nerves and the coating 35 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
756
will be thus in close proximity to neural tissues. The results shown in Figure S10 suggest that
757
such coatings do not induce neurotoxicity and are able to keep the surrounding neural tissue
758
healthy.
759 760 761 762 763 764 765
Figure 9. In vitro evaluation of zwitterionic hydrogels on macrophage cells. (a) Fluorescence images at 10x magnification of RAW 264.7 cells on zwitterionic hydrogels and on PI samples, showing nuclei in blue and actin in red (scale bar = 100 µm). (b) Quantification of the adhesion of RAW 264.7 macrophages on zwitterionic hydrogels H2, H5, H6 and on PI samples after 24h of culture. Box and whisker plots represent the median values and interquartile ranges of the number of adherent cells per cm2 (whiskers represent the maximum 36 ACS Paragon Plus Environment
Page 36 of 44
Page 37 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
766 767 768 769 770 771 772 773 774 775 776 777
Langmuir
and minimum values obtained). * = p < 0.05, ** = p < 0.01. (c) Spontaneous nitric oxide production of cells seeded on zwitterionic hydrogels and PI samples for 24 h, provided also with reference values of non- activated cells cultured on tissue culture polystyrene (PS, negative control), and cells cultured on tissue culture polystyrene and activated by means of LPS stimulation (positive control). Box and whisker plots represent the median values and interquartile ranges of the concentration of nitric oxide produced (whiskers represent the maximum and minimum values obtained). (d) Morphological difference between nonstimulated and LPS-stimulated macrophages seeded on tissue culture polystyrene (PS). LPSstimulated macrophages show activation-dependent morphology, with higher adhesion and spreading, compared to non-stimulated ones. Nuclei are stained in blue and actin in red (scale bar = 100 µm).
778
779
CONCLUSION
780
Due to their biocompatibility, flexibility and patternability with lithographic and dry etching
781
techniques, polyimides (PI) are widely used both as implant encapsulation materials and as
782
substrates for implanted neural interfaces. Despite these promising properties, they cannot
783
prevent the formation of a fibrotic capsule. Several approaches have been reported aiming at
784
reducing the formation of a scar-like tissue around the implant. The inhibition of protein and
785
cell adhesion by means of non-biofouling coatings is one of these strategies. Moreover, it has
786
been shown that the undesired host response to implants is also determined by the mechanical
787
mismatch between the implant and the surrounding tissue. To this aim, in this work we
788
presented a strategy for covalently attaching carboxybetaine polyzwitterionic hydrogel
789
coatings to PI substrates, obtained by means of a photoactivated process. These coatings were
790
featured by low stiffness values in the range of the neural tissues, for their possible future
791
application as coatings for neural interfaces. Modified PI plates were characterized by a set of
792
physico-chemical methods to evidence the presence of coatings, to visualize the completeness
793
of the surface coverage by hydrogels, and to characterize the layer thickness and Young’s
794
modulus. The in vitro response of both fibroblasts and macrophages (the main cell types
37 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
795
involved in the foreign body response) was assessed. The zwitterionic hydrogel coatings
796
reduced the adhesion of both cell lines respect to PI control, showing almost no cytotoxicity
797
and a clear correlation with the hydrogel stiffness. Moreover, the hydrogel layers did not
798
induce macrophages activation, evaluated through the quantification of nitric oxide
799
production. These results demonstrate the non-biofouling properties, low stiffness and UV
800
patternability of zwitterionic hydrogels and thus establish the foundation for their possible in
801
vivo investigation as coatings for PI-based neural interfaces.
802 803
SUPPORTING INFORMATION
804
The Supporting Information is available free of charge on DOI:
805
Syntheses of monomers M1 and M2 (Schemes S1 and S2), 1H NMR spectra of M1 and M2
806
(Figures S1 and S2), Calibration curve for M2 absorbance vs. concentration (Figure S3), 1H
807
NMR spectra of copolymers C1 and C2 (Figures S4 and S5), ATR-FTIR of C1 and C2
808
(Figure S6), ATR-FTIR of PI and Pluronic F-127 (Figure S7), WLI determination of hydrogel
809
thickness (Figure S8), AFM force vs indentation indentation curves for hydrogel surfaces
810
(Figure S9), ). In vitro assessment with neural model SH-SY5Y cell line (Figure S10), and
811
experimental conditions for optimizing the fabrication of hydrogel layers (Table S1).
812 813
ACKNOWLEDGEMENT
814
This work was supported by the M2Neural project (http://www.m2neural.eu), funded in the
815
FP7 M-ERA.NET Transnational framework. In addition, this work was also supported by the
816
Slovak Research and Development Agency under contract numbers APVV-14-0858 as well
817
as the VEGA Grant Agency under the contract no. 2/0059/16.
818
38 ACS Paragon Plus Environment
Page 38 of 44
Page 39 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
Langmuir
819
REFERENCES
820 821 822 823 824 825 826 827 828 829 830 831 832 833 834 835 836 837 838 839 840 841 842 843 844 845 846 847 848 849 850 851 852 853 854 855 856 857 858 859 860 861 862 863 864 865 866 867 868
1. Giselbrecht, S.; Rapp, B. E.; Niemeyer, C. M. The Chemistry of Cyborgs—Interfacing Technical Devices With Organisms. Angew. Chem. Int. Ed. 2013, 52, 13942-13957. 2. Navarro, X.; Krueger, T. B.; Lago, N.; Micera, S.; Stieglitz, T.; Dario, P. A Critical Review of Interfaces With The Peripheral Nervous System For The Control Of Neuroprostheses And Hybrid Bionic Systems. J. Peripher. Nerv. Syst. 2005, 10, 229-258. 3. Grill, W. M.; Norman, S. E.; Bellamkonda, R. V. Implanted Neural Interfaces: Biochallenges And Engineered Solutions. Annu. Rev. Biomed. Eng. 2009, 11, 1-24. 4. Rothschild, R. M. Neuroengineering Tools/Applications For Bidirectional Interfaces, Brain– Computer Interfaces, And Neuroprosthetic Implants–A Review Of Recent Progress. Front. Neuroeng. 2010, 3, 112. 5. Raspopovic, S.; Capogrosso, M.; Petrini, F. M.; Bonizzato, M.; Rigosa, J.; Di Pino, G.; Carpaneto, J.; Controzzi, M.; Boretius, T.; Fernandez, E. Restoring Natural Sensory Feedback In Real-Time Bidirectional Hand Prostheses. Sci. Transl. Med. 2014, 6, 222ra19-222ra19. 6. Hochberg, L. R.; Bacher, D.; Jarosiewicz, B.; Masse, N. Y.; Simeral, J. D.; Vogel, J.; Haddadin, S.; Liu, J.; Cash, S. S.; van der Smagt, P. Reach And Grasp By People With Tetraplegia Using A Neurally Controlled Robotic Arm. Nature 2012, 485, 372-375. 7. Fekete, Z.; Pongrácz, A. Multifunctional Soft Implants To Monitor And Control Neural Activity In The Central And Peripheral Nervous System: A Review. Sensor. Actuat. B-Chem. 2017, 243, 12141223. 8. Myllymaa, S.; Myllymaa, K.; Korhonen, H.; Lammi, M. J.; Tiitu, V.; Lappalainen, R. Surface Characterization And In Vitro Biocompatibility Assessment Of Photosensitive Polyimide Films. Colloid. Surface. B 2010, 76, 505-511. 9. Sun, Y.; Lacour, S.; Brooks, R.; Rushton, N.; Fawcett, J.; Cameron, R. Assessment Of The Biocompatibility Of Photosensitive Polyimide For Implantable Medical Device Use. J. Biomed. Mater. Res. A 2009, 90, 648-655. 10. Mercanzini, A.; Cheung, K.; Buhl, D. L.; Boers, M.; Maillard, A.; Colin, P.; Bensadoun, J.-C.; Bertsch, A.; Renaud, P. Demonstration Of Cortical Recording Using Novel Flexible Polymer Neural Probes. Sensor. Actuat. A-Phys. 2008, 143, 90-96. 11. Cheung, K. C.; Renaud, P.; Tanila, H.; Djupsund, K. Flexible Polyimide Microelectrode Array For In Vivo Recordings And Current Source Density Analysis. Biosens. Bioelectron. 2007, 22, 1783-1790. 12. Hollenberg, B. A.; Richards, C. D.; Richards, R.; Bahr, D. F.; Rector, D. M. A MEMS Fabricated Flexible Electrode Array For Recording Surface Field Potentials. J. Neurosci. Meth. 2006, 153, 147153. 13. Grill, W. M.; Mortimer, J. T. Stability Of The Input-Output Properties Of Chronically Implanted Multiple Contact Nerve Cuff Stimulating Electrodes. IEEE Trans. Rehabil. Eng. 1998, 6, 364-373. 14. Lago, N.; Yoshida, K.; Koch, K. P.; Navarro, X. Assessment Of Biocompatibility Of Chronically Implanted Polyimide And Platinum Intrafascicular Electrodes. IEEE Trans. Biomed. Eng. 2007, 54, 281-290. 15. Boretius, T.; Badia, J.; Pascual-Font, A.; Schuettler, M.; Navarro, X.; Yoshida, K.; Stieglitz, T. A Transverse Intrafascicular Multichannel Electrode (TIME) To Interface With The Peripheral Nerve. Biosens. Bioelectron. 2010, 26, 62-69. 16. Cutrone, A.; Del Valle, J.; Santos, D.; Badia, J.; Filippeschi, C.; Micera, S.; Navarro, X.; Bossi, S. A Three-Dimensional Self-Opening Intraneural Peripheral Interface (SELINE). J. Neural Eng. 2015, 12, 016016. 17. Wurth, S.; Capogrosso, M.; Raspopovic, S.; Gandar, J.; Federici, G.; Kinany, N.; Cutrone, A.; Piersigilli, A.; Pavlova, N.; Guiet, R. Long-Term Usability And Bio-Integration Of Polyimide-Based Intra-Neural Stimulating Electrodes. Biomaterials 2017, 122, 114-129. 18. Birla, R. Introduction To Tissue Engineering: Applications And Challenges. John Wiley & Sons: 2014.
39 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
869 870 871 872 873 874 875 876 877 878 879 880 881 882 883 884 885 886 887 888 889 890 891 892 893 894 895 896 897 898 899 900 901 902 903 904 905 906 907 908 909 910 911 912 913 914 915 916 917 918
19. Onuki, Y.; Bhardwaj, U.; Papadimitrakopoulos, F.; Burgess, D. J. A review Of The Biocompatibility Of Implantable Devices: Current Challenges To Overcome Foreign Body Response. J. Diabetes Sci. Technol. 2008, 2, 1003-1015. 20. Rao, S. S.; Winter, J. Adhesion Molecule-Modified Biomaterials For Neural Tissue Engineering. Front. Neuroeng. 2009, 2, 6. 21. Ahmed, I.; Liu, H. Y.; Mamiya, P. C.; Ponery, A. S.; Babu, A. N.; Weik, T.; Schindler, M.; Meiners, S. Three-Dimensional Nanofibrillar Surfaces Covalently Modified With Tenascin-C-Derived Peptides Enhance Neuronal Growth In Vitro. J. Biomed. Mater. Res. A 2006, 76, 851-860. 22. Righi, M.; Bossi, S.; Puleo, G.; Giudetti, G.; Wieringa, P.; Cutrone, A.; Micera, S. Surface Modification of Polyimide Thin Films for Peripheral Invasive Neural Interfaces. J. Med. Devices 2013, 7, 020937. 23. He, W.; McConnell, G. C.; Schneider, T. M.; Bellamkonda, R. V. A Novel Anti-Inflammatory Surface For Neural Electrodes. Adv. Mater. 2007, 19, 3529-3533. 24. Straley, K. S.; Heilshorn, S. C. Design And Adsorption Of Modular Engineered Proteins To Prepare Customized, Neuron-Compatible Coatings. Front. Neuroeng. 2009, 2, 9. 25. Abidian, M. R.; Martin, D. C. Multifunctional Nanobiomaterials For Neural Interfaces. Adv. Funct. Mater. 2009, 19, 573-585. 26. Moxon, K. A.; Kalkhoran, N. M.; Markert, M.; Sambito, M. A.; McKenzie, J.; Webster, J. T. Nanostructured Surface Modification Of Ceramic-Based Microelectrodes To Enhance Biocompatibility For A Direct Brain-Machine Interface. IEEE Trans. Biomed. Eng. 2004, 51, 881889. 27. Moxon, K.; Hallman, S.; Aslani, A.; Kalkhoran, N.; Lelkes, P. Bioactive Properties Of Nanostructured Porous Silicon For Enhancing Electrode To Neuron Interfaces. J. Biomater. Sci. Polym. Ed. 2007, 18, 1263-1281. 28. Lu, Y.; Wang, D.; Li, T.; Zhao, X.; Cao, Y.; Yang, H.; Duan, Y. Y. Poly (Vinyl Alcohol)/Poly (Acrylic Acid) Hydrogel Coatings For Improving Electrode–Neural Tissue Interface. Biomaterials 2009, 30, 4143-4151. 29. Gutowski, S. M.; Shoemaker, J. T.; Templeman, K. L.; Wei, Y.; Latour, R. A.; Bellamkonda, R. V.; LaPlaca, M. C.; García, A. J. Protease-Degradable PEG-Maleimide Coating With On-Demand Release Of IL-1Ra To Improve Tissue Response To Neural Electrodes. Biomaterials 2015, 44, 5570. 30. Heo, D.; Song, S.; Kim, H.; Lee, Y.; Ko, W.; Lee, S.; Lee, D.; Park, S.; Zhang, L.; Kang, J. Multifunctional Hydrogel Coatings On The Surface Of Implantable Cuff Electrode For Improving Electrode-Peripheral Nerve Tissue Interfaces. Acta Biomater. 2016, 39, 25-33. 31. Kim, D.-H.; Martin, D. C. Sustained Release Of Dexamethasone From Hydrophilic Matrices Using PLGA Nanoparticles For Neural Drug Delivery. Biomaterials 2006, 27, 3031-3037. 32. Hilborn, J.; Bjursten, L. M. A New And Evolving Paradigm For Biocompatibility. J. Tissue Eng. Regen. Med. 2007, 1, 110-119. 33. Minev, I. R.; Musienko, P.; Hirsch, A.; Barraud, Q.; Wenger, N.; Moraud, E. M.; Gandar, J.; Capogrosso, M.; Milekovic, T.; Asboth, L. Electronic Dura Mater For Long-Term Multimodal Neural Interfaces. Science 2015, 347, 159-163. 34. Lacour, S. P.; Courtine, G.; Guck, J. Materials And Technologies For Soft Implantable Neuroprostheses. Nat. Rev. Mater. 2016, 1, 16063. 35. Blakney, A. K.; Swartzlander, M. D.; Bryant, S. J. The Effects Of Substrate Stiffness On The In Vitro Activation Of Macrophages And In Vivo Host Response To Poly (Ethylene Glycol)-Based Hydrogels. J. Biomed. Mater. Res. A 2012, 100 (6), 1375. 36. Okay, O. General Properties Of Hydrogels. In Hydrogel sensors and actuators, Springer: 2009, pp 1-14. 37. Rao, S. S.; Han, N.; Winter, J. O. Polylysine-Modified PEG-Based Hydrogels To Enhance The Neuro–Electrode Interface. J. Biomater. Sci. Polym. Ed. 2011, 22, 611-625.
40 ACS Paragon Plus Environment
Page 40 of 44
Page 41 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
919 920 921 922 923 924 925 926 927 928 929 930 931 932 933 934 935 936 937 938 939 940 941 942 943 944 945 946 947 948 949 950 951 952 953 954 955 956 957 958 959 960 961 962 963 964 965 966 967 968 969 970
Langmuir
38. Park, S. J.; Lee, Y. J.; Heo, D. N.; Kwon, I. K.; Yun, K.-S.; Kang, J. Y.; Lee, S. H. Functional Nerve Cuff Electrode With Controllable Anti-Inflammatory Drug Loading And Release By Biodegradable Nanofibers And Hydrogel Deposition. Sensor. Actuat. B-Chem. 2015, 215, 133-141. 39. Spencer, K. C.; Sy, J. C.; Ramadi, K. B.; Graybiel, A. M.; Langer, R.; Cima, M. J. Characterization of Mechanically Matched Hydrogel Coatings to Improve the Biocompatibility of Neural Implants. Sci. Rep. 2017, 7. 40. Barz, M.; Luxenhofer, R.; Zentel, R.; Vicent, M. J. Overcoming The Peg-Addiction: Well-Defined Alternatives To Peg, From Structure-Property Relationships To Better Defined Therapeutics. Polym. Chem. 2011, 2, 1900-1918. 41. Li, L.; Chen, S.; Jiang, S. Protein Interactions With Oligo(Ethylene Glycol) (OEG) Self-Assembled Monolayers: OEG Stability, Surface Packing Density And Protein Adsorption. J. Biomater. Sci. Polym. Ed. 2007, 18, 1415-1427. 42. Knop, K.; Hoogenboom, R.; Fischer, D.; Schubert, U. S. Poly(ethylene glycol) in Drug Delivery: Pros and Cons as Well as Potential Alternatives. Angew. Chem. Int. Ed. 2010, 49, 6288-6308. 43. Jiang, S.; Cao, Z. Ultralow-Fouling, Functionalizable, and Hydrolyzable Zwitterionic Materials and Their Derivatives for Biological Applications. Adv. Mater. 2010, 22, 920-932. 44. Chen, S.; Zheng, J.; Li, L.; Jiang, S. Strong Resistance of Phosphorylcholine Self-Assembled Monolayers to Protein Adsorption: Insights into Nonfouling Properties of Zwitterionic Materials. J. Am. Chem. Soc. 2005, 127, 14473-14478. 45. Sin, M.-C.; Chen, S.-H.; Chang, Y. Hemocompatibility of zwitterionic Interfaces And Membranes. Polym J 2014, 46, 436-443. 46. Shao, Q.; He, Y.; White, A. D.; Jiang, S. Difference in Hydration between Carboxybetaine and Sulfobetaine. J Phys. Chem. B 2010, 114, 16625-16631. 47. Wu, J.; Lin, W.; Wang, Z.; Chen, S.; Chang, Y. Investigation Of The Hydration Of Nonfouling Material Poly(Sulfobetaine Methacrylate) By Low-Field Nuclear Magnetic Resonance. Langmuir 2012, 28, 7436-7441. 48. Liu, P.; Huang, T.; Liu, P.; Shi, S.; Chen, Q.; Li, L.; Shen, J. Zwitterionic Modification Of Polyurethane Membranes For Enhancing The Anti-Fouling Property. J. Colloid Interf. Sci. 2016, 480, 91-101. 49. Chien, H. W.; Cheng, P. H.; Chen, S. Y.; Yu, J.; Tsai, W. B. Low-fouling And Functional Poly(Carboxybetaine) Coating Via A Photo-Crosslinking Process. Biomater. Sci. 2017, 5, 523-531. 50. Lin, X.; Fukazawa, K.; Ishihara, K. Photoreactive Polymers Bearing a Zwitterionic Phosphorylcholine Group for Surface Modification of Biomaterials. ACS Appl. Mater. Inter. 2015, 7, 17489-17498. 51. Konno, T.; Hasuda, H.; Ishihara, K.; Ito, Y. Photo-immobilization Of A Phospholipid Polymer For Surface Modification. Biomaterials 2005, 26, 1381-1388. 52. Sakuragi, M.; Tsuzuki, S.; Obuse, S.; Wada, A.; Matoba, K.; Kubo, I.; Ito, Y. A Photoimmobilizable Sulfobetaine-Based Polymer For A Nonbiofouling Surface. Mater. Sci. Eng. C 2010, 30, 316-322. 53. Sobolčiak, P.; Popelka, A.; Mičušík, M.; Sláviková, M.; Krupa, I.; Mosnáček, J.; Tkáč, J.; Lacík, I.; Kasák, P. Photoimmobilization Of Zwitterionic Polymers On Surfaces To Reduce Cell Adhesion. J. Colloid Interf. Sci. 2017, 500, 294-303. 54. Zhao, C.; Zhao, J.; Li, X.; Wu, J.; Chen, S.; Chen, Q.; Wang, Q.; Gong, X.; Li, L.; Zheng, J. Probing Structure-Antifouling Activity Relationships Of Polyacrylamides And Polyacrylates. Biomaterials 2013, 34, 4714-4724. 55. Mary, P.; Bendejacq, D. D.; Labeau, M.-P.; Dupuis, P. Reconciling Low- and High-Salt Solution Behavior of Sulfobetaine Polyzwitterions. J. Phys. Chem. B 2007, 111, 7767-7777. 56. Abraham, S.; Unsworth, L. D. Multi-Functional Initiator And Poly (Carboxybetaine Methacrylamides) For Building Biocompatible Surfaces Using “Nitroxide Mediated Free Radical Polymerization” Strategies. J. Polym. Sci. A Polym. Chem. 2011, 49, 1051-1060. 57. Ito, Y.; Hasuda, H.; Sakuragi, M.; Tsuzuki, S. Surface Modification Of Plastic, Glass And Titanium By Photoimmobilization Of Polyethylene Glycol For Antibiofouling. Acta Biomater. 2007, 3, 10241032.
41 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
971 972 973 974 975 976 977 978 979 980 981 982 983 984 985 986 987 988 989 990 991 992 993 994 995 996 997 998 999 1000 1001 1002 1003 1004 1005 1006 1007 1008 1009 1010 1011 1012 1013 1014
58. Cross, S. E.; Jin, Y.-S.; Rao, J.; Gimzewski, J. K. Nanomechanical Analysis Of Cells From Cancer Patients. Nat. Nanotechnol. 2007, 2, 780-783. 59. Matzke, R.; Jacobson, K.; Radmacher, M. Direct, High-Resolution Measurement Of Furrow Stiffening During Division Of Adherent Cells. Nat. Cell Biol. 2001, 3, 607-610. 60. Hutter, J. L.; Bechhoefer, J. Calibration Of Atomic-Force Microscope Tips. Rev. Sci. Instrum. 1993, 64, 1868-1873. 61. Ferrera, D.; Canale, C.; Marotta, R.; Mazzaro, N.; Gritti, M.; Mazzanti, M.; Capellari, S.; Cortelli, P.; Gasparini, L. Lamin B1 Overexpression Increases Nuclear Rigidity In Autosomal Dominant Leukodystrophy Fibroblasts. FASEB J. 2014, 28, 3906-3918. 62. Bilodeau, G. Regular Pyramid Punch Problem. J. Appl. Mech. 1992, 59, 519-523. 63. Roger, P.; Renaudie, L.; Le Narvor, C.; Lepoittevin, B.; Bech, L.; Brogly, M. Surface Characterizations Of Poly(Ethylene Terephthalate) Film Modified By A Carbohydrate-Bearing Photoreactive Azide Group. Eur. Polym. J. 2010, 46, 1594-1603. 64. Mrsevic, M.; Düsselberg, D.; Staudt, C. Synthesis and Characterization Of A Novel Carboxyl Group Containing (Co)Polyimide With Sulfur In The Polymer Backbone. Beilstein J. Org. Chem. 2012, 8, 776-786. 65. Vigano, C.; Ruysschaert, J.-M.; Goormaghtigh, E. Sensor Applications Of Attenuated Total Reflection Infrared Spectroscopy. Talanta 2005, 65, 1132-1142. 66. Cho, S.-J.; Nguyen, T.; Boo, J.-H. Polyimide Surface Modification by Using Microwave Plasma for Adhesion Enhancement of Cu Electroless Plating. J. Nanosci. Nanotechnol. 2011, 11, 5328-5333. 67. Lieu Le, N.; Quilitzsch, M.; Cheng, H.; Hong, P.-Y.; Ulbricht, M.; Nunes, S. P.; Chung, T.-S. Hollow Fiber Membrane Lumen Modified By Polyzwitterionic Grafting. J. Membrane Sci.2017, 522, 1-11. 68. Inoue, Y.; Ishihara, K., Reduction Of Protein Adsorption On Well-Characterized Polymer Brush Layers With Varying Chemical Structures. Colloid. Surface. B 2010, 81, 350-357. 69. Stach, M.; Kroneková, Z.; Kasák, P.; Kollár, J.; Pentrák, M.; Mičušík, M.; Chorvát, D.; Nunney, T. S.; Lacík, I. Polysulfobetaine Films Prepared By Electrografting Technique For Reduction Of Biofouling On Electroconductive Surfaces. Appl. Surf. Sci. 2011, 257, 10795-10801. 70. Kasák, P.; Kroneková, Z.; Krupa, I.; Lacík, I. Zwitterionic Hydrogels Crosslinked With Novel Zwitterionic Crosslinkers: Synthesis And Characterization. Polymer 2011, 52, 3011-3020. 71. Zhang, Z.; Chao, T.; Liu, L.; Cheng, G.; Ratner, B. D.; Jiang, S. Zwitterionic hydrogels: An In Vivo Implantation Study. J. Biomater. Sci. Polym. Ed. 2009, 20, 1845-1859. 72. Zhang, L.; Cao, Z.; Bai, T.; Carr, L.; Ella-Menye, J.-R.; Irvin, C.; Ratner, B. D.; Jiang, S. Zwitterionic Hydrogels Implanted In Mice Resist The Foreign-Body Reaction. Nat. Biotechnol. 2013, 31, 553556. 73. Khandwekar, A. P.; Patil, D. P.; Shouche, Y. S.; Doble, M. The Biocompatibility Of Sulfobetaine Engineered Polymethylmethacrylate By Surface Entrapment Technique. J. Mater. Sci. Mater. Med. 2010, 21, 635-646. 74. Irwin, E.; Saha, K.; Rosenbluth, M.; Gamble, L.; Castner, D.; Healy, K. Modulus-Dependent Macrophage Adhesion And Behavior. J. Biomater. Sci. Polym. Ed. 2008, 19, 1363-1382. 75. Lyle D. B.; Shallcross J. C.; Durfor C. N.; Hitchins V. M.; Breger J. C.; Langone J. J. Screening Biomaterials For Stimulation Of Nitric Oxide-Mediated Inflammation. J. Biomed. Mater. Res. A 2008, 90, 82-93. 76. Feyerabend, F.; Siemers, C.; Willumeit, R.; Rösler, J. Cytocompatibility Of A Free Machining Titanium Alloy Containing Lanthanum. J. Biomed. Mater. Res. A 2009, 90, 931-939.
1015
42 ACS Paragon Plus Environment
Page 42 of 44
Page 43 of 44 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
1016
Langmuir
ABSTRACT GRAPHIC
1017
43 ACS Paragon Plus Environment
Langmuir 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17 18 19 20 21 22 23 24 25 26 27 28 29 30 31 32 33 34 35 36 37 38 39 40 41 42 43 44 45 46 47 48 49 50 51 52 53 54 55 56 57 58 59 60
150x70mm (123 x 113 DPI)
ACS Paragon Plus Environment
Page 44 of 44