Principles of capnography:
By the Beer-Lambert law:
$$\text{Absorbance} = \Delta L \cdot \epsilon^{\text{wavelength}}_{gas} \cdot P_{gas}$$
IR light is shone through 2 chambers - the sample chamber and reference chamber (contains no CO2, for calibration); the absorbance is used to calculate the CO2 partial pressure.
Sample can be side-stream
- sample taken from thin tube connected to ventilator circuit
- increases delay to ~3 seconds
- sampler can be placed e.g. beneath a hudson mask
...or main-stream
- sample taken directly from circuit
- adds dead space

A capnograph waveform has 4 phases:
- Phase 1: Inspiration and the first part of expiration, where anatomical dead space gas is expired. No CO2.
- Phase 2: mixed dead space gas and alveolar gas
- Phase 3: pure alveolar gas.
- Phase 0: inspiration washes out CO2 from monitor
Sources of error:
- Blockage by secretions / condensation
- Ambient IR light
- N2O absorbance
- Collision broadening from high FiO2 or FiN2O
Limitations
- False positive CO2 from gastrict gas post BVM ventilation
- Increased dead space will widen PaCO2-EtCO2 gap
Ventilation and perfusion info obtained from trace:
- Height (EtCO2): composed of
- PaCO2 (\uparrow\) with \(\downarrow V_A\) or \(\uparrow\) CO2 generation e.g. malignant hyperthermia.
- PaCO2 - EtCO2 gap which \(\propto\) dead space or high V/Q lung units. Usually <5mmHg. Gap widened with \(\uparrow\) anatomical/instrumental dead space, PE, fall in cardiac output.
- Frequency = respiratory rate
- Rhythm = presence of abormal breathing patterns, e.g. dyssynchrony or Cheyne-Stokes
- Baseline = Presence of rebreathing (closed ventilator circuit \(\to\) exhausted lime, open ventilator circuit \(\to\ \ V_D > V_T\))
- Shape
- Decreased phase II slope, increased phase II slope, "shark fin" appearance \(\to\) prolonged mixing of alveolar and dead space gas \(\to\) time constant heterogeneity (e.g. obstructive lung disease)
- Curate clefts \(\to\) dyssynchrony
- Irregular waveform \(\to\) intermittent blockage by secretions, leakage