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Tmspma

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TMSPMA is a laboratory chemical compound used as a silane coupling agent. It serves to improve the adhesion between inorganic surfaces and organic polymers. The core function of TMSPMA is to provide a chemical link between these two materials.

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Lab products found in correlation

Irgacure 2959, by Merck Group (2 mentions) Omnicure series 2000, by Excelitas (2 mentions) Pegda, by JenKem Technology (2 mentions) Omnicure s2000, by Excelitas (1 mentions) Oxygen plasma cleaner, by Harrick (1 mentions) Penicillin streptomycin, by Thermo Fisher Scientific (1 mentions) Fetal bovine serum (fbs), by Thermo Fisher Scientific (1 mentions) Focalseal ls100, by Sanofi (1 mentions) Benzoyl peroxide, by Merck Group (1 mentions) Methyl methacrylate, by Merck Group (1 mentions) Ammonia solution 25, by Merck Group (1 mentions) Nunc thermanox coverslips, by Thermo Fisher Scientific (1 mentions) Double distilled water, by Carl Roth (1 mentions) 1 phenyl 1 2 propanedione ppd, by Merck Group (1 mentions) Brain heart infusion broth, by Carl Roth (1 mentions)

Spelling variants of this product

3-(trimethoxysilyl)propyl methacrylate (TMSPMA) (11 citations)

12 protocols using tmspma

1

Photomask-Guided Hydrogel Patterning

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Photomask designs were first created using computer aided design (CAD)
software. These masks were designed to have equal alternating transparent and
opaque sections for each individual size. Three mask types consisting of 60, and
120 μm alternating patterns, and an OHSU logo mask were fabricated
(Output City). Hydrogel constructs were fabricated by dispensing 10 μl of
GelMA hydrogel precursor onto a TMSPMA (3-(Trimethoxysilyl)propyl methacrylate)
(Sigma) coated glass slide. The hydrogel precursor was then compressed to 100
μm thick disks following previous methods [5 (link)]. This hydrogel disk was then photocrosslinked under UV light with
a power of 850 mW for 30 s and at a distance of 8.5 cm. Patterned hydrogel was
formed by covering the sample with an individual photomask prior to photo
crosslinking. The resulting hydrogel was rinsed with DPBS to remove any
remaining hydrogel precursor, as illustrated in Fig. 2.
Ha M., Athirasala A., Tahayeri A., Menezes P.P, & Bertassoni L.E. (2019). Micropatterned hydrogels and cell alignment enhance the odontogenic potential of stem cells from apical papilla in-vitro. Dental materials : official publication of the Academy of Dental Materials, 36(1), 88-96.
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2

Hydrogel Microwell Array Fabrication

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UV‐photocrosslinkable PEGDA (Jenkem Technology) of molecular weight 3500 Da were mixed with photoinitiator Irgacure 2959, HHEMP (Sigma‐Aldrich) and diluted with 1xPBS to form a prepolymer solution comprising of the photoinitiator. The patterned PDMS stamp was placed on an evenly distributed film of prepolymer solution on a TMSPMA (Sigma‐Aldrich)‐treated cover slip, with two coverslips placed on both sides as spacers. Photopolymerization was achieved by irradiating the set‐up with UV light of 320‐500 nm and at an intensity of 4.96 W/cm2 for 30 seconds using the OmniCure®Series 2000 curing station (Lumen Dynamics) as previously optimized. After photopolymerization, the PDMS stamp was peeled from the fabricated hydrogel microwell arrays, which were submerged in 70% ethanol for 2 hours to remove excess prepolymer solution. Hydrogel microwell arrays were subsequently washed thrice with PBS and stored in sterile PBS under aseptic conditions prior to cell seeding.
Tan J.J., Common J.E., Wu C., Ho P.C, & Kang L. (2019). Keratinocytes maintain compartmentalization between dermal papilla and fibroblasts in 3D heterotypic tri‐cultures. Cell Proliferation, 52(5), e12668.
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3

PAAm Hydrogel Bonding on PEN Film

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For bonding of the PAAm-based hydrogel on the PEN film, the interdigitated electrode evaporated PEN substrates (Teijin DuPont Films) were treated with oxygen plasma for 3 min to generate hydrophilic surface functional groups on the film. Then, PEN substrates were immersed in the TMSPMA (Sigma-Aldrich, 440159) solution for 3 min to silanize the substrates. The TMSPMA solution was prepared by adding 1 ml of TMSPMA in 200 ml of ethanol and subsequent addition of 6 ml of acetic acid [10% (v/v) in water] under gentle stirring. After surface functionalization, the PEN substrate was washed thoroughly with ethanol and dried under a stream of nitrogen gas. Thereafter, the pregel solution was polymerized under UV irradiation (365 nm, 15 W) for 25 min on the functionalized PEN substrates. The polymerized gel was immersed in the same concentration of LiCl batch overnight to absorb LiCl solution and reach equilibrium state.
Yeom J., Choe A., Lim S., Lee Y., Na S, & Ko H. (2020). Soft and ion-conducting hydrogel artificial tongue for astringency perception. Science Advances, 6(23), eaba5785.
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4

Hydrogel Microwell Arrays Fabrication

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To bond the hydrogels onto the glass surface, the following procedure was carried out. The microscopic glass slide was soaked in 0.4% v/v 3-(trimethoxysilyl) propyl methacrylate (TMS-PMA) (Sigma Aldrich, Singapore) for 12 h to provide bonding sites on the glass surface [54 (link)]. The glass side was then rinsed with water and dried at 70 °C for 2 h. Two coverslips were stacked up as spacers on the glass slide. Then the PDMS stamp was placed on top of the two coverslips (Figure 7B). To make the PDMS surface wettable, the PDMS stamp was treated using an oxygen plasma cleaner (Harrick Plasma, Ithaca, NY, USA) for 3 min. Afterwards, 50 μL of 5.0% w/v MeHA prepolymer solution was carefully added into the gap between the PDMS stamp and glass slide using a micropipette. The prepolymer solution was then exposed to ultraviolet (UV) radiation of 4.3 W/cm2 for 40 s at 4 cm to the light source OmniCure s2000 (Excelitas Technologies, Waltham, MA, USA). After exposure, the PDMS stamp was peeled off from the surface, coverslip spacers were removed, and the formed hydrogel microwell array was placed in 10 mL of PBS solution.
The fabrication of hydrogel microwell arrays containing DPSCs is presented separately in Section 2.6.
Park S., Huang N.W., Wong C.X., Pan J., Albakr L., Gu J, & Kang L. (2021). Microstructured Hyaluronic Acid Hydrogel for Tooth Germ Bioengineering. Gels, 7(3), 123.
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5

Hydrogel Cell Culture Protocol

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Hydrogel prepolymer solution was prepared as previously described. Seven microliters of precursor solution was then pipetted between a 3-(trimethoxysilyl) propyl methacrylate (TMSPMA; Sigma-Aldrich)–coated glass slide and a petri dish separated with a 300-μm spacer. The prepolymer solutions were then photocrosslinked for 4 min via visible light. Next, 40 μl of corneal fibroblast cell solution (2 × 106 cells/ml) was seeded on each sample. After 45-min incubation, 360 μl of cell culture media was added to each sample, and they were maintained at 37°C and 5% CO2 for 5 days. In addition, cells at the same density were also seeded inside 24-well tissue culture plates. As the commercial control, the tissue culture well plates were coated with ReSure sealant, and the same cell density (40 μl, 2 × 106 cells/ml) was seeded in each well.
Shirzaei Sani E., Kheirkhah A., Rana D., Sun Z., Foulsham W., Sheikhi A., Khademhosseini A., Dana R, & Annabi N. (2019). Sutureless repair of corneal injuries using naturally derived bioadhesive hydrogels. Science Advances, 5(3), eaav1281.
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6

Fabrication of Hydrogel Microwell Arrays

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UV-photocrosslinkable GelMA synthesized earlier or PEGDA (Jenkem Technology, USA) of molecular weight 3500 Da was mixed with photoinitiator Irgacure 2959, HHEMP (Sigma-Aldrich, USA) and diluted with 1× PBS to form a prepolymer solution containing the photoinitiator. The patterned PDMS stamp was placed on an evenly distributed film of prepolymer solution on a TMSPMA (Sigma-Aldrich, New York, NY, USA)-treated cover slip, with 2 coverslips set on both sides as spacers. Photopolymerization was attained by irradiating the set-up with UV light of 320–500 nm and at an intensity of 4.96 W/cm2 for 30 s using the OmniCure®Series 2000 curing station (Lumen Dynamics, Canada) as previously optimized. After photopolymerization, the PDMS stamp was removed from the fabricated hydrogel microwell arrays, which were submerged in 70% ethanol for 2 h to remove excess prepolymer solution. Hydrogel microwell arrays were then washed thrice with PBS and stored in sterile PBS under aseptic conditions prior to cell seeding.
Tan J.J., Nguyen D.V., Common J.E., Wu C., Ho P.C, & Kang L. (2021). Investigating PEGDA and GelMA Microgel Models for Sustained 3D Heterotypic Dermal Papilla and Keratinocyte Co-Cultures. International Journal of Molecular Sciences, 22(4), 2143.
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7

Hydrogel-based Cardiac Cell Culture

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Hydrogels were formed by placing a 7-μl drop of hydrogel precursor in a spacer with 150-μm height and covered by a glass slide coated with 3-(trimethoxysilyl) propyl methacrylate (TMSPMA, Sigma-Aldrich). Hydrogel precursors were then photocrosslinked for 20 s using a Genzyme FocalSeal LS100 xenon light source. Primary rat CMs (3.5 × 104 cells/scaffold) were seeded on the surface of the hydrogels and placed in 24-well plates with 400 μl of growth medium (DMEM supplemented with 10% fetal bovine serum (FBS, Invitrogen) and 1% penicillin/streptomycin (Invitrogen)). 2D cultures were maintained at 37 °C in a 5% CO2 humidified atmosphere, for 10 days and culture medium was replaced every 48 h.
Noshadi I., Walker B.W., Portillo-Lara R., Shirzaei Sani E., Gomes N., Aziziyan M.R, & Annabi N. (2017). Engineering Biodegradable and Biocompatible Bio-ionic Liquid Conjugated Hydrogels with Tunable Conductivity and Mechanical Properties. Scientific Reports, 7, 4345.
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8

Bioadhesive Hydrogel Seeding for Cell Culture

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Hydrogels were formed by pipetting 7 μl of precursor solution between a 3-(trimethoxysilyl) propyl methacrylate (TMSPMA, Sigma-Aldrich) coated glass slide and a glass coverslip separated with a 100 μm spacer. Bioadhesive hydrogels were photocrosslinked using visible light for 60 sec. The hydrogels were seeded with W-20–17 cells (5 × 106 cells/ml) and kept at 37 °C, 5% CO2 for 5 days 60
Sani E.S., Lara R.P., Aldawood Z., Bassir S.H., Nguyen D., Kantarci A., Intini G, & Annabi N. (2019). An Antimicrobial Dental Light Curable Bioadhesive Hydrogel for Treatment of Peri-Implant Diseases. Matter, 1(4), 926-944.
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9

Synthesis of SiO2, ZrO2, and Composite Materials

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The chemicals for the SiO2 synthesis were Tetraethyl Orthosilicate (CAS: 78-10-4), Acetic Acid Glacial (CAS: 64-19-7 |100056), and Ethanol 98% (CAS: 628-97-7) received from (EMSURE® ACS, ISO, Reag. Ph Eur, Merck, Rahway, NJ, USA), and PEG 400 (CAS: 25322-68-3) purchased from PT Brataco Chemical, Indonesia. The chemicals for the ZrO2 synthesis were Zirconium Oxychloride Octahydrate 99% AR (Loba Chemie PVT. Ltd., Mumbai, India, CAS: 13520-92-8), Ammonia Solution 25% (Merck, CAS: 631-61-8), and Aquadest (CAS: 7732-18-5). The chemicals for the ZrO2-SiO2 mix were obtained from both precursors of SiO2 and ZrO2. The chemicals for the composite were Methyl Methacrylate (stabilized for synthesis, Merck) and Benzoyl Peroxide (CAS: 94-36-0) for synthesis (Merck), and two different types of silane of (3-Mercaptopropyl) trimethoxysilane (MPTS, Sigma-Aldrich, St. Louis, MO, USA, CAS: 40372-72) and 3-(trimethoxysilyl) propyl methacrylate 98% (TMSPMA, Sigma-Aldrich, CAS: 97 2530-85).
Widodo P., Mulyawan W., Djustiana N, & Joni I.M. (2023). Synthesis and Characterization of Zirconia–Silica PMMA Nanocomposite for Endodontic Implants. Dentistry Journal, 11(3), 57.
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10

Mechanical Evaluation of Bioink Scaffolds

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Compression and lap shear tests were performed to evaluate the mechanical properties of the scaffolds in this work. An Instron 5542 mechanical tester (MA, USA) was used to perform the experiments. To perform the compression tests, the scaffolds were fabricated in cylindrical shape using a polydimethylsiloxane (PDMS; Dow, MI, USA) mold with 6 mm diameter and 5 mm height. To avoid overfilling, a glass slide was placed on top of the filled mold and the bioink was photo-crosslinked through a glass slide as described before. The sample was then removed from the mold and placed between the compression plates of the device as shown in Figure 3. A compression rate of 1mm/min was then applied and the compression modulus was calculated from the slope of a fitted line interpolating the stress-strain data up to 10% strain. The lap shear tests were performed based on the ASTM F2255-05 standard [47 ]. Rectangular pieces of porcine muscle (13 mm × 10 mm) were cut and glued into glass slides using cyanoacrylate adhesive. The bioink was then printed onto the tissue with 13 mm × 10 mm × 2 mm dimensions, covered with 3-(trimethoxysilyl) propyl methacrylate (TMSPMA; Sigma-Aldrich) coated glass slide, and photo-crosslinked as described. The samples were subsequently secured on the mechanical testing device using grips (Figure 3) and pulled in shear at a rate of 1 mm/min until failure occurred.
Besson A, & Yong V.W. (2000). Involvement of p21Waf1/Cip1 in Protein Kinase C Alpha-Induced Cell Cycle Progression. Molecular and Cellular Biology, 20(13), 4580-4590.
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