Tissue heating during RF/microwave hyperthermia and ablation is governed by the Pennes bioheat equation: heat diffuses through tissue, is deposited by the applicator, and is carried away by blood perfusion, which acts as a distributed heat sink.
∂T/∂t = α∇²T − ω(T − T_a) + q(x,z)
α — thermal diffusivity of tissue
ω — perfusion (heat-sink) coefficient — small in bulk
tissue, MUCH larger in the ring of cells around
a real blood vessel (fast-flowing blood clamps
nearby tissue close to arterial temperature T_a)
T_a — arterial blood temperature, 37°C
q — power deposited by the applicator (Gaussian, centered)
The grid below is solved on every frame with an explicit finite-difference stencil (5-point Laplacian, several sub-steps per frame for numerical stability). A large vessel running past the tumor adds a second, spatially-local sink term — this is the real "heat-sink effect" interventional radiologists worry about: even with the applicator at full power, tissue immediately next to a vessel can stay tens of degrees cooler than the rest of the target, leaving a cold streak of under-treated tumor that survives ablation.
- Heating power — strength of the applicator's Gaussian heat source at the target center.
- Blood flow (vessel cooling) — how strongly the vessel clamps nearby tissue toward 37°C; 0 removes the vessel's effect entirely, 1 is a large, fast-flowing vessel.
- Vessel distance / diameter — geometry of the vessel relative to the treatment target; closer and wider vessels cut a bigger cold streak through the coverage.
- Coverage readout — the fraction of the target-zone (dashed ring) that has reached the 43°C thermal-damage threshold used clinically (CEM43 dosimetry) — this is what a heat-sink cold spot drives down.