FAQ / Question log

Kanzler Biologicals documents a commercial preclinical research and development project focused on artificial-heart engineering, mechanical circulatory support and regenerative cardiovascular research, active since 2017.

No. This is preclinical engineering documentation — not an approved medical device and not medical advice. No treatment, purchase or clinical application is offered.

Transparency is the point: every value on this site is labelled as concept, target or confirmed, and open validation questions are listed rather than hidden.

The systemic circuit needs higher outlet pressure and larger stroke volume; the pulmonary circuit runs at lower pressure with gentler flow. A single chamber for both tasks would either overload the lungs or under-supply the body.

A pulsatile membrane pump (silicone-based membrane) via an electric linear drive (roller screw), serving the systemic circuit only: concept stroke 8–12 mm, chamber volume up to 130 ml, outlet pressure up to 210 mmHg (short-term design maximum, not a normal operating pressure).

It adds pulsatile energy to the continuous baseline flow and can act as a pressure buffer — it exists solely for pulsatility, not as a replacement for the main pump. Fill volume 40–50 ml; its beat frequency follows the main pump.

Approx. 21 mm diameter, approx. 10 mm body length, continuous operation with a rotor/impeller, pressure rise up to 20 mmHg, flow rate up to 13 l/min.

A two-stage safety relief: bypass valve 1 diverts flow toward the pulse chamber when outlet pressure or flow plausibility thresholds are exceeded; bypass valve 2 is a second safety path if bypass 1 is insufficient. The final relief route still needs architectural definition and hydraulic verification.

Physiological pulmonary circulation runs well below systemic pressure; the microaxial pump is designed for a pressure rise up to 20 mmHg. The actual operating point must be patient-adaptive — people with pre-existing pulmonary hypertension run higher than any rigid limit.

Pressure before/after the pump, flow, RPM, temperature, valve state and pulse chamber pressure — with cross-sensor plausibility checks (e.g. high RPM with low flow signals possible blockage, cavitation, clot or sensor drift).

A staged response: reduce power → bypass 1 → bypass 2 → alarm → defined safe mode. Each stage still requires bench and fault-injection testing.

No. Each stage of the staged response, and every sensor plausibility rule, still needs dedicated bench and fault-injection testing before it can be considered validated.

An implantable battery module: 14.8 V nominal, approx. 4.7 Ah, approx. 70 Wh (concept), with a BMS for cell balancing, thermal monitoring and overcharge/deep-discharge protection.

Through TET-based inductive charging: 3 equally sized external coils and 3 equally sized implanted receiver coils as 3 independent pairs (no intermediate coil), with 2 redundant electronics modules per unit. Frequency is still open (150 kHz is only a preliminary investigation value), target efficiency 85%, coil size still open, designed to minimise tissue heating.

Misalignment can turn electrical transfer into a thermal problem. Safe charge windows and stop criteria still need to be defined through tissue-equivalent phantom testing across distance, offset and angle.

Confirmed: pump dimensions, chamber volumes, battery voltage/capacity/energy, target efficiency. Still open, and explicitly labelled rather than guessed: TET frequency and coil size, heat-spreader fluid and pump, bus voltage (14.8 V vs. a possible ~22 V), emergency-pump electrical power, pulmonary operating pressure.

Material validation, sterilisation strategy, biocompatibility, hemocompatibility, electrical safety, software validation, risk management and long-duration evidence — none of which exist yet.

No. Explicit disclaimer: preclinical R&D project, not an approved medical device, not medical advice. Evidence ratings and specs describe engineering targets, not clinical proof.