PMB (MPC polymer) does not have a specific biological target. Its mechanism of action is physicochemical: the highly hydrophilic, zwitterionic surface reduces non-specific interactions with bacteria and proteins, thereby inhibiting bacterial adhesion. It is not bactericidal; it only prevents bacterial attachment without affecting planktonic bacteria. [1]
MPC itself is a functional monomer, and its targets are biological interfaces. MPC polymers exhibit strong affinity for natural phospholipids in plasma, constructing a biomembrane-like structure on the material surface when in contact with plasma. This surface can suppress protein adsorption, subsequent platelet adhesion, and activation, thereby exerting antithrombotic effects. MPC polymers improve blood compatibility by increasing the amount of free water in the hydrogels, which prevents protein conformational change.
MPC does not exert its effects through a specific pharmacological target. Instead, its mechanism of action is biophysical: the phosphorylcholine group induces bulk-like behavior in surrounding water molecules, creating a hydration layer that suppresses protein adsorption and cell adhesion when in contact with biological fluids such as plasma or whole blood. This property is central to its function as a biocompatible material.

PMB-coated sutures significantly reduced the initial adhesion of both MRSA and MSSA compared to non-coated sutures, with reductions of 93% and 79%, respectively (p < 0.001). There was no significant difference in the number of planktonic bacteria between coated and non-coated sutures, indicating a bacteriostatic (anti-adhesive) rather than bactericidal effect. [1]
Fluorescence microscopy (SYTO 9 staining) showed that the area of adherent MRSA and MSSA on PMB-coated sutures was significantly reduced by 72% and 74%, respectively (p < 0.001). SEM images confirmed that few bacterial colonies adhered to the PMB-coated surface, while many colonies adhered to the non-coated surface. [1]
After 24 hours of culture (biofilm formation conditions), PMB-coated sutures significantly suppressed biofilm formation for both MRSA and MSSA, as shown by fluorescence microscopy and SEM (p < 0.001). [1]

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Protein Adsorption Inhibition: MPC copolymer surfaces significantly inhibit plasma protein adsorption. On poly(BMA) surfaces, fibrinogen adsorbs abundantly in a patchy pattern; while on PMB with 0.30 MPC unit mole fraction, all adsorbed proteins including albumin, fibrinogen, γ-globulin, and high molecular-weight kininogen are drastically reduced compared to poly(BMA). Platelet Adhesion Inhibition: MPC polymer surfaces effectively reduce platelet adhesion and aggregation. SEM images show that poly(BMA) surfaces are completely covered with a fibrin net with numerous adhered blood cells, while PMB surfaces show almost no fibrin deposition. Cell Protective Activity: Poly-MPC protects human primary corneal epithelial cells from desiccation damage. Poly-MPC and hypromellose show better retention on HCE-F cell membranes than trehalose or hyaluronic acid. Prolonged Coagulation Time: In whole blood coagulation time tests, PMB-coated surfaces show significantly prolonged coagulation time (28±2.6 minutes) compared to glass (8.4±0.46 minutes) and poly(BMA) (9.6±1.3 minutes) (P<0.01). Anti-coagulation Factor Activity: MPC polymers significantly reduce the adsorbed amount of high molecular-weight kininogen, a coagulation factor, on the surface.

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In vitro, MPC polymers are used to modify surface properties of materials, effectively reducing protein-surface interactions and inhibiting the adhesion of bacteria such as Staphylococcus aureus and Porphyromonas gingivalis. MPC has also been shown to reduce IL-8 production. As a monomer, it can be polymerized to create fully zwitterionic polymer networks for use as gel electrolytes in lithium-based batteries.

In a mouse subcutaneous implantation model (C57BL/6J mice), MRSA suspension (5.0 × 10⁸ bacteria/mL) was inoculated onto PMB-coated and non-coated sutures before implantation. After 1, 3, and 7 days, biofilm formation was suppressed on PMB-coated sutures compared to non-coated sutures, as observed by fluorescence microscopy and SEM. No mice exhibited skin disorders, poor wound healing, or death during the study. [1]

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Skin Barrier Repair: In a hairless mouse skin barrier damage model, topical application of MPC copolymer-containing formulations (C/L Poly (AA-Co-MPC 5w%) 0.5% and 10w% 0.5%) significantly reduces skin erythema index, water loss values, and the number of mast cells in dermal and subcutaneous layers (P<0.05), indicating that MPC improves skin barrier damage. Prolonged Plasma Retention: PMPC conjugation to RB005, a DNA aptamer targeting soluble activated coagulation factor IX, significantly prolongs the in vivo plasma retention of the aptamer.

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In vivo, MPC-based polymers and hydrogels have been evaluated for their biocompatibility and resistance to foreign body responses. MPC-modified surfaces show significantly reduced inflammatory responses and fibrosis when implanted in animal models. The compound is also used as a component in drug delivery systems to prolong circulation time and reduce immunogenicity.

Phospholipid Adsorption Assay: MPC polymer membranes are immersed in a liposomal solution of dipalmitoyl phosphatidylcholine. Differential scanning calorimetry and XPS analysis confirm that adsorbed DPPC molecules on the PMB surface assume an organized structure like that for a multi-/bi-layer membrane. AFM directly observes that liposomes adsorbed on PMB maintain their spherical shape without morphological changes. Phospholipid adsorption from human plasma shows that the amount of adsorbed phosphatidylcholine increases with increasing MPC unit mole fraction in the polymer.

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For in vitro protein adsorption assays, surfaces coated with MPC polymers are incubated with protein solutions (e.g., fibrinogen, albumin) at 37°C for 1-2 hours. The amount of adsorbed protein is quantified using colorimetric assays such as the BCA assay or by radiolabeling. For bacterial adhesion studies, surfaces are incubated with bacterial suspensions (e.g., S. aureus) for 1-4 hours at 37°C, and adherent bacteria are counted by colony-forming unit (CFU) enumeration or fluorescence microscopy.

Cell Membrane Interaction Assessment: Using human primary corneal epithelial cells, the interaction of poly-MPC with the cell membrane is evaluated by the sodium dodecyl sulfate damage protection assay or the displacement of the cell-binding lectin concanavalin A. Desiccation Damage Protection Assay: HCE-F cells are pre-treated with poly-MPC, hyaluronic acid, hypromellose, or trehalose before exposure to desiccating conditions. Cell survival is evaluated by a colorimetric assay. Results show that poly-MPC, HA, and HPMC either alone or in association protect corneal cells from desiccation significantly better than trehalose alone or in association with HA. Cytotoxicity/Viability Assessment: In Huh7.5 cells, MPC-related materials show no marked cytotoxicity at concentrations below 80 μM.

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For in vitro cell-based experiments, MPC polymers are evaluated for biocompatibility using mammalian cell lines such as fibroblasts or endothelial cells. Cells are seeded onto MPC-coated surfaces and cultured for 24-72 hours. Cell viability is assessed using MTT or resazurin assays. Cell adhesion and morphology are examined by fluorescence microscopy. Cytokine production (e.g., IL-8, TNF-α) is measured by ELISA to assess inflammatory responses.

Mouse subcutaneous implantation model: Twelve 8-week-old male C57BL/6J mice were used. Mice were intraperitoneally injected with an anesthetic mixture (medetomidine 0.38 mg/kg, midazolam 2.0 mg/kg, butorphanol 2.5 mg/kg). Hair was removed, and subcutaneous pockets were created on both sides of the back. PMB-coated sutures were implanted on the right side and non-coated sutures on the left side. MRSA suspension (5.0 × 10⁸ bacteria/mL) was inoculated onto the sutures before implantation. Incisions were closed with 5-0 nylon suture. No antibiotics were used post-operatively. After 1, 3, and 7 days, animals were euthanized, and sutures were removed for fluorescence microscopy and SEM observation. [1]

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Skin Barrier Damage Model: A skin irritation animal model is produced by applying sodium dodecyl sulfate to the backs of hairless mice for 1 week, with experimental materials applied topically for 1 week during the same period. On day 7, experimental groups containing MPC copolymers (E2: C/L Poly (AA-Co-MPC 5w%) 0.5%; E3: C/L Poly (AA-Co-MPC 10w%) 0.5%) show significantly lower values of skin erythema index and water capacity (P<0.05) and significantly lower transepidermal water loss values (P<0.05) compared to the vehicle control group, with remarkably reduced mast cell appearance in dermal and subcutaneous layers.

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In vivo animal studies for MPC are typically conducted in rodent models. MPC-coated implants or MPC-based hydrogels are implanted subcutaneously or in other relevant sites. After 1-4 weeks, the implants and surrounding tissues are harvested for histological analysis to assess inflammation, fibrosis, and foreign body response. Biocompatibility and integration are evaluated by comparing with uncoated controls.

Physicochemical Properties: Molecular weight 295.27 g/mol, consensus Log P -1.37 (hydrophilic), water solubility 33.8 mg/mL (very soluble), TPSA 94.7 Ų. Absorption and Distribution: In silico prediction shows high GI absorption but no BBB permeation; predicted to be a P-gp substrate. Metabolism: In silico prediction shows MPC is not an inhibitor of CYP1A2, CYP2C19, CYP2C9, CYP2D6, or CYP3A4. Bioavailability: Abbott Bioavailability Score is 0.55 (probability of F > 10% in rat). Storage Conditions: Powder is stable for 3 years at -20°C; solutions are stable for 6 months at -80°C and 1 month at -20°C. MPC monomer should be stored at 2-8°C.

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Pharmacokinetic data for MPC as a monomer are not applicable, as it is polymerized into biomaterials rather than administered as a free drug. When used as a coating or in hydrogels, the polymer is retained locally at the site of application. Degradation products are expected to be metabolized through normal biochemical pathways. MPC itself is a biochemical reagent that can be used as a biological material or organic compound for life science research.

The study notes that PMB coating has bacteriostatic (anti-adhesive) effects without bactericidal activity, indicating it does not kill bacteria and therefore poses no health-related risks associated with antimicrobial resistance or cytotoxicity. The medical applicability and safety of MPC polymers are well established in the literature. [1]

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Low Cytotoxicity: MPC polymers exhibit low toxicity due to their zwitterionic phosphorylcholine group. In Huh7.5 cells, MPC-related materials show no marked cytotoxicity at concentrations below 80 μM. Skin Compatibility: MPC copolymers show improvement effects on skin barrier damage in hairless mice, with reduced erythema index, indicating good skin tolerance. In Silico Predicted Toxicity: According to admetSAR 2.0, PAINS alert count is 0 (no pan-assay interference structures), Brenk structural alert count is 3, synthetic accessibility score is 3.89 (fairly easy to synthesize).

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MPC is generally considered biocompatible and non-toxic when used as a polymer in medical devices. The monomer should be handled with standard laboratory precautions, as it may cause skin and eye irritation. Specific LD₅₀ values for MPC are not well-documented in the literature, but it is classified as a biochemical reagent for research use only.

[1]. 2-Methacryloyloxyethyl Phosphorylcholine Polymer Coating Inhibits Bacterial Adhesion and Biofilm Formation on a Suture: An In Vitro and In Vivo Study. Biomed Res Int. 2020 Oct 1:2020:5639651.

Coating method: PMB was dissolved in ethanol at 1.0 wt%. Sutures were immersed in the solution, air-dried, then dried at 50°C for 30 min. Sutures were sterilized with ethylene oxide gas. [1]
Characterization: X-ray photoelectron spectroscopy (XPS) confirmed PMB coating by detecting phosphorus atoms (P2p peak at 133 eV) only on coated sutures. Rhodamine 6G staining (which selectively adsorbs to phospholipids) showed strong fluorescence on coated sutures. The absolute amount of phosphorus on PMB-coated sutures was 6.2 μg/cm vs. 0.09 μg/cm on non-coated sutures (p < 0.001). [1]
Mechanical properties: PMB coating did not affect suture diameter (0.61 ± 0.00 vs. 0.60 ± 0.01 mm), weight (0.36 ± 0.05 vs. 0.36 ± 0.03 mg), or maximum tensile strength (170 ± 4 vs. 170 ± 3 N). Static water contact angle was significantly lower on coated sutures (31 ± 5° vs. 38 ± 6°, p < 0.01), indicating increased hydrophilicity. [1]
Mechanism: The zwitterionic phosphorylcholine groups in PMB form a hydration layer via electrostatic interactions with water molecules, creating a physical barrier that resists protein adsorption and bacterial adhesion. [1]

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MPC (CAS 67881-98-5) is a research-grade polymer monomer and biochemical reagent, not an FDA-approved pharmaceutical drug. Its primary applications are in biomaterials science for creating biocompatible surfaces, drug delivery systems, and tissue engineering scaffolds. MPC is also used as a monomer to produce zwitterionic polymer networks. No clinical trials or approved therapeutic indications exist for this compound.

C11H22NO6P

295.27

295.118

67881-98-5

67881-99-6

128934

White to light yellow solid powder

143-148°C

-2.95

0

6

10

19

354

0

P(=O)([O-])(OC([H])([H])C([H])([H])OC(C(=C([H])[H])C([H])([H])[H])=O)OC([H])([H])C([H])([H])[N+](C([H])([H])[H])(C([H])([H])[H])C([H])([H])[H]

ZSZRUEAFVQITHH-UHFFFAOYSA-N

InChI=1S/C11H22NO6P/c1-10(2)11(13)16-8-9-18-19(14,15)17-7-6-12(3,4)5/h1,6-9H2,2-5H3

2-(2-methylprop-2-enoyloxy)ethyl 2-(trimethylazaniumyl)ethyl phosphate

2-Methacryloyloxyethyl phosphorylcholine; 67881-98-5; 2-(Methacryloyloxy)ethyl 2-(Trimethylammonio)ethyl Phosphate; 2-Moep; UNII-59RU860S8D;

2934.99.9001

Powder      -20°C    3 years

                     4°C     2 years

In solvent   -80°C    6 months

                  -20°C    1 month

Room temperature (This product is stable at ambient temperature for a few days during ordinary shipping and time spent in Customs)

DMSO: 100 mg/mL (338.67 mM)

Note: Listed below are some common formulations that may be used to formulate products with low water solubility (e.g. < 1 mg/mL), you may test these formulations using a minute amount of products to avoid loss of samples.

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Injection Formulation 1: DMSO : Tween 80： Saline = 10 : 5 : 85 (i.e. 100 μL DMSO stock solution → 50 μL Tween 80 → 850 μL Saline)
*Preparation of saline: Dissolve 0.9 g of sodium chloride in 100 mL ddH ₂ O to obtain a clear solution.
Injection Formulation 2: DMSO : PEG300 ：Tween 80 : Saline = 10 : 40 : 5 : 45 (i.e. 100 μL DMSO → 400 μLPEG300 → 50 μL Tween 80 → 450 μL Saline)
Injection Formulation 3: DMSO : Corn oil = 10 : 90 (i.e. 100 μL DMSO → 900 μL Corn oil)
Example: Take the Injection Formulation 3 (DMSO : Corn oil = 10 : 90) as an example, if 1 mL of 2.5 mg/mL working solution is to be prepared, you can take 100 μL 25 mg/mL DMSO stock solution and add to 900 μL corn oil, mix well to obtain a clear or suspension solution (2.5 mg/mL, ready for use in animals).

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Injection Formulation 4: DMSO : 20% SBE-β-CD in saline = 10 : 90 [i.e. 100 μL DMSO → 900 μL (20% SBE-β-CD in saline)]
*Preparation of 20% SBE-β-CD in Saline (4°C，1 week): Dissolve 2 g SBE-β-CD in 10 mL saline to obtain a clear solution.
Injection Formulation 5: 2-Hydroxypropyl-β-cyclodextrin : Saline = 50 : 50 (i.e. 500 μL 2-Hydroxypropyl-β-cyclodextrin → 500 μL Saline)
Injection Formulation 6: DMSO : PEG300 : castor oil : Saline = 5 : 10 : 20 : 65 (i.e. 50 μL DMSO → 100 μLPEG300 → 200 μL castor oil → 650 μL Saline)
Injection Formulation 7: Ethanol : Cremophor : Saline = 10： 10 : 80 (i.e. 100 μL Ethanol → 100 μL Cremophor → 800 μL Saline)
Injection Formulation 8: Dissolve in Cremophor/Ethanol (50 : 50), then diluted by Saline
Injection Formulation 9: EtOH : Corn oil = 10 : 90 (i.e. 100 μL EtOH → 900 μL Corn oil)
Injection Formulation 10: EtOH : PEG300：Tween 80 : Saline = 10 : 40 : 5 : 45 (i.e. 100 μL EtOH → 400 μLPEG300 → 50 μL Tween 80 → 450 μL Saline)

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Oral Formulation 1: Suspend in 0.5% CMC Na (carboxymethylcellulose sodium)
Oral Formulation 2: Suspend in 0.5% Carboxymethyl cellulose
Example: Take the Oral Formulation 1 (Suspend in 0.5% CMC Na) as an example, if 100 mL of 2.5 mg/mL working solution is to be prepared, you can first prepare 0.5% CMC Na solution by measuring 0.5 g CMC Na and dissolve it in 100 mL ddH2O to obtain a clear solution; then add 250 mg of the product to 100 mL 0.5% CMC Na solution, to make the suspension solution (2.5 mg/mL, ready for use in animals).

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Oral Formulation 3: Dissolved in PEG400
Oral Formulation 4: Suspend in 0.2% Carboxymethyl cellulose
Oral Formulation 5: Dissolve in 0.25% Tween 80 and 0.5% Carboxymethyl cellulose
Oral Formulation 6: Mixing with food powders

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Note: Please be aware that the above formulations are for reference only. InvivoChem strongly recommends customers to read literature methods/protocols carefully before determining which formulation you should use for in vivo studies, as different compounds have different solubility properties and have to be formulated differently.

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 (Please use freshly prepared in vivo formulations for optimal results.)