20-Bio-A1 Biomaterials and Biocompatibility · May 2018
Nivaar worked solution (AI-drafted; not reviewed by a licensed engineer)
Paper format: National Exams, May 2018 — 04-Bio-A1 Biomaterials and Biocompatibility. Three hours, open book, any non-communicating calculator. Six questions of equal value (20 marks each, 100 marks total for a complete paper); five constitute a complete exam paper and only the first five appearing in the answer book are marked. All six are solved here, because this set is a study resource rather than an examination script. Most questions require an essay-format answer (materials selection, host response, surface/mechanical characterization); Question 6 additionally asks for an engineering interpretation of a small stress–strain data set, so it quotes and reasons from descriptive statistics computed from the given numbers while still answering in the flowing prose the question calls for.
Reference texts (the books an open-book candidate should have on the desk for this subject):
Question text not reproduced: the examination questions are © Engineers and Geoscientists BC. Open the official past paper (linked at the top of this page) to read the question, then follow the worked solution below.
The part (b) interpretation is read directly from the printed figure, reproduced below as Figure 2.1.
Large-diameter arterial replacement succeeds with Dacron/PTFE largely because high volumetric flow and correspondingly high wall shear rate keep the luminal surface relatively free of adherent thrombus, and because the lumen is large enough that even a thin layer of neointima or mural thrombus on the graft wall removes only a small fraction of the cross-sectional flow area. Below about 5–6 mm diameter, three problems compound: first, flow rate and wall shear stress in this size range are much lower, which favours platelet adhesion, aggregation, and thrombus formation on the synthetic (non-endothelialized) luminal surface; second, none of the standard synthetic grafts spontaneously develop a confluent, functional endothelial monolayer — the natural, non-thrombogenic lining every native vessel has — so the graft surface remains permanently thrombogenic rather than becoming biologically “invisible” to blood; and third, the mechanical compliance mismatch between a stiff synthetic tube and the compliant native artery it is anastomosed to creates a localized, disturbed-flow zone at the suture line that drives intimal hyperplasia (smooth-muscle-cell proliferation), progressively narrowing the graft precisely where the smaller lumen can least tolerate it. Because even a thin layer of thrombus or hyperplastic tissue removes a much larger fraction of a small lumen than of a large one, small-diameter grafts occlude at a rate that has made them clinically unusable, and native vein (with its own endothelium and compliant wall) remains the only reliable option. The goal has not been achieved because no material yet reliably delivers all three requirements together — a durable, functional, non-thrombogenic endothelium; mechanical compliance matched to the native artery; and adequate long-term structural durability — simultaneously in a low-flow, low-shear environment.
[Figure not reproduced: Fibrinogen adsorption versus plasma concentration for the control and PEO-modified surfaces, as printed on the May 2018 examination paper. See the official exam paper or the cited reference text.]
On the control surface the curve is not a simple saturating isotherm. Fibrinogen adsorption is highest (≈0.083 µg/cm²) from the most dilute plasma, falls steeply — by about 45% — to a minimum of ≈0.045 µg/cm² by 2–5% plasma, and then rises only slightly (≈0.052 at 20%). This is the classic Vroman effect. In very dilute plasma there is little competition for surface sites, so fibrinogen — abundant, and adsorbing rapidly and avidly to an unmodified synthetic surface — takes a large share of them. As the plasma concentration rises, more surface-active, higher-affinity proteins that arrive later (high-molecular-weight kininogen and other contact-phase proteins) compete for the surface and progressively displace the initially adsorbed fibrinogen, so the net amount retained falls to a lower, roughly constant level. That retained layer is still substantial, and adsorbed fibrinogen can unfold and expose its platelet-binding γ-chain (GPIIb/IIIa recognition) sequence, directly promoting platelet adhesion and aggregation — so a surface that retains this much fibrinogen at physiological plasma concentrations is a marker of high thrombogenic potential. On the PEO-modified surface adsorption is low at every concentration and rises only slowly and monotonically (≈0.005 to ≈0.018 µg/cm²), with no Vroman peak at all, because very little protein reaches the surface for later proteins to displace: PEO’s long, highly hydrated, flexible surface chains create a steric-exclusion/hydration-layer barrier — the mobile chains sterically hinder an approaching protein from reaching the underlying surface, and the strongly bound hydration layer around the hydrophilic PEO chains makes protein displacement of that water thermodynamically unfavourable. Read together, the two curves show PEO grafting cutting fibrinogen adsorption by roughly 17× in the most dilute plasma, about 3.8× at 5% and about 2.9× at 20% plasma; the gap narrows slowly as the concentration rises, but the modified surface stays well below the control across the whole range shown.
The significance for blood-compatible materials development is direct: because platelet adhesion and activation correlate strongly with the amount and conformational state of adsorbed fibrinogen, a surface chemistry (like PEO grafting) that suppresses fibrinogen adsorption at all physiologically relevant plasma concentrations is predicted to have substantially lower thrombogenicity than the unmodified control — a materials-based, “passive” route to improved haemocompatibility that is mechanistically distinct from, and complementary to, the active endothelial-seeding and heparin-immobilization strategies for the small-diameter graft problem of part (a). The control curve also carries a methodological lesson: the amount of fibrinogen found on a surface depends strongly on the plasma concentration at which it is measured, so blood-compatibility screening must be done in (near-)physiological plasma rather than inferred from a single dilute-solution or single-protein measurement.
Phospholipid-mimetic coatings — most commonly built from phosphorylcholine (PC), the same zwitterionic headgroup that dominates the outer leaflet of the native red-blood-cell and vascular endothelial-cell membrane — work by presenting blood with a surface chemistry it is evolutionarily “used to” rather than a foreign polymer surface. The PC headgroup carries an equal, closely-spaced positive (choline) and negative (phosphate) charge, giving a net-neutral but highly polar group that binds an exceptionally tight, ordered hydration layer through ion–dipole interactions; that bound-water layer resists displacement by an approaching plasma protein by essentially the same thermodynamic mechanism as the PEO hydration barrier in part (b), but achieved through dense zwitterionic charge pairing rather than long flexible chain mobility — a second, chemically distinct route to the same functional outcome (low protein adsorption, low platelet activation). Because a native cell membrane surface is, by definition, non-thrombogenic to the blood that constantly contacts it, a synthetic surface that closely reproduces its outer chemistry has strong a priori biological plausibility as a low-fouling, blood-compatible coating; this reasoning is already commercialized in 2-methacryloyloxyethyl phosphorylcholine (MPC) polymer coatings used on some coronary stents, catheters, and extracorporeal circuit tubing.
A 4 mm femoro-popliteal bypass is the clinical scenario in which the graft-diameter problem of part (a) is most acute, and a PEO- or phosphorylcholine-grafted luminal coating (parts (b)/(c)) is exactly the kind of surface-chemistry intervention that could be combined with the compliance-matched wall design and endothelial-seeding/heparin strategies discussed for that problem, since none of these approaches individually has yet solved the small-diameter graft problem on its own.
