Introduction
Toward consensus
Acquisition
Muscle | Options | Electrode 1 (Anode) | Electrode 2 (Cathode) |
---|---|---|---|
Diaphragm | Bilaterally long Unilaterally long Unilaterally short | MCL subcostal Left Xiphoid AAL 6th/7th/8th ICS Right | MCL subcostal Right MAL subcostal Right AAL 7th/8th/9th ICS Right |
Parasternal | Bilaterally Unilaterally | 2nd/3rd ICS Left 2nd rib, sternal edge | 2nd/3rd ICS Right 3rd rib, 2 cm lateral to sternal edge |
Sternocleidomastoid | Mastoid/Clavicular notch | Lower 1/3 portion, 2 cm apart | |
Scalene | Posterior triangle of the neck at the level of the cricoid process | ||
Ext. oblique | Combined | AAL, 1/2 costal margin à Iliac crest | MCL medially from anode |
Int. oblique |
Electrode positioning
Interelectrode distance
Technical considerations
Preprocessing
Specifics | Common pitfalls | Best practice | |
---|---|---|---|
ECG removal | |||
High-pass filtering | Specific for first ‘raw’ data checks and preliminary step for some preprocessing methods (gating) The higher the ratio between respiratory and cardiac signal power, the lower the required cutoff frequency to reduce impact of cardiac activity on the filtered signal (such as in small-distance electrode setups and parasternal EMG when muscle activation is strong | Distortion of the spectrum Reduction in EMG amplitude Absence of respiratory EMG amplitude in the filtered signal when there is cardiac interference and/or very weak respiratory muscle activation | If used as the sole method, a high cutoff frequency should be employed and adjusted to minimize impact of cardiac activity Mean Absolute Value (MAV) is recommended to obtain the respiratory waveform in cases where QRS peaks are still present in the resulting signal Lower cutoff frequencies (< 50Hz) should be combined with other preprocessing techniques to fully remove the QRS complex |
Gating | Envelope calculation when EMG amplitude is to be maintained Requires robust detection of R-peaks | Cannot be used with tachycardia Substantial loss of temporal information Not suitable for detecting respiratory onset/offset with high precision | Pan-Tompkins algorithm should be used to detect R-peaks Combination with 20 Hz high-pass filter to remove P and T waves Window length should be adjusted to the duration of the QRS complex Appropriate gate-filling techniques must be used (interpolation or median) |
Wavelet | Go-to method for ECG removal in far-distance electrode setups (with strong ECG interference) when resp muscle activation is small Best method when R-peaks cannot be robustly detected (e.g., many ectopic beats, patients with arrhythmias) | Inadequate setting of Fs, level of decomposition, thresholds Thresholding might cutoff large EMG activity bursts | Pre-filtering is not required Number of decomposition levels depends on sampling frequency and should be adjusted to the P-/T- waves and motion artifacts (10–20 Hz): 5 levels for fs of 1000 Hz, increase/decrease level when fs doubles/halves Resulting wavelet-bands and thresholds should be checked visually Daubechies 2 and 4 wavelets have demonstrated good performance in denoising respiratory EMG [29, 35, 36] Fixed threshold; start with a threshold set at 4.5 times the standard deviation of the decomposition level (σk) |
Envelope | |||
General recommendation: Use centered window with length 250 ms, deviate when application demands | |||
Root Mean Square (RMS) | Most generally used Power of the signal can be used based on RMS (and compared with that obtained by spectral methods) | N/A | Step size of the moving window should be considered (1 sample step is feasible) |
Average Rectified Value (ARV) | Less affected by high amplitude peaks (like remaining QRS artifacts) than RMS | ||
Mean Absolute Value (MAV) | Combination with HPF | ||
Fixed sample entropy (fSampEn) | More robust than RMS and ARV, i.e., less affected by high amplitude peaks caused by remaining artifacts | Step size of the moving window: 1 sample step can be computationally expensive (for fSampEn) | Application directly to raw data, no other filtering needed Embedded dimension (m = 1) Tolerance value (r) set to 0.2–0.3 times the standard deviation of the sEMG signal |
Low-frequency artifact removal
ECG removal
Envelope signal
Postprocessing
Key parameter | Definition/calculation | Potential application/benefits | Notes & limitations |
---|---|---|---|
Magnitude of muscle activity | |||
Amplitude | Difference between maximum and minimum value during. one breath (either including or excluding the baseline) Using the 95th and 5th percentile to calculate this difference may be more robust | Assessing changes in absolute magnitude of muscle activity within a single recording | Low amplitude does not imply low muscle activity and vice versa Only comparable within short-time recordings Does not enable between-patient or between-recording comparisons |
Amplitude normalized to maximum breathing effort | Amplitude divided by maximum amplitude obtained during maximum inspiratory maneuver | Assessing changes in relative muscle activity Improves sEMG amplitude interpretability | Maximum inspiratory maneuvers could be challenging to perform in critically ill patients and multiple repetitions are required Maximum amplitude should be re-obtained for a new recording |
Amplitude normalized to maximum amplitude within recording | Amplitude divided by maximum amplitude obtained over a given measurement (without ensuring maximum effort) | Assessing changes in relative muscle activity within a patient during a recording Improves sEMG amplitude interpretability | Maximum amplitude should be re-obtained for a new recording It does not enable between-patient comparisons or within-patient comparisons across multiple recordings |
EMG-time product | Area under the sEMG envelope, per breath or per time unit | Less sensitive to remaining artifacts than computing breathwise sEMG amplitudes | Dependent on whether the baseline is included in computation Affected by sEMG onset and offset definitions |
Estimation of mechanical output | |||
Estimated breathing effort | Pmus = k x sEMG, with conversion factor k obtained from patient-specific measures (end-expiratory occlusion or model-based) | Translates muscle activity to mechanical output | k needs to be re-evaluated for a new recording Assumes a linear relationship between muscle activity and output |
Timing of muscle activity | |||
Time-to-peak | Time from onset to peak sEMG | Suggested to reflect respiratory drive | Onset/offset is not binary; no clear definition exists (see text for approaches) Increase in sEMG activity may not be linear Unclear comparability between patients |
Duration of muscle activity | Time from sEMG onset to offset | Informs about the duration of muscle activation | Onset/offset is not binary; no clear definition exists (see text for approaches) |
Phase angle | Phase lag between sEMG onset (or offset) and start (or end) of ventilator pressurization Phase lag between onset (or offset) of multiple sEMG signals | Assessing patient-ventilator interaction Assessing activation patterns (different muscles) | Onset/offset of sEMG is not binary; no clear definition exists (see text for approaches) |
Absolute time delay | Time delay (in ms) between sEMG onset (or offset) and start (or end) of ventilator pressurization Time delay (in ms) between onset (or offset) of multiple sEMG signals | Assessing patient-ventilator interaction Assessing activation patterns (different muscles) | Onset/offset of sEMG is not binary; no clear definition exists (see text for approaches) Does not correct for duration of activity/pressurization such as with phase angle |
Fatigue | |||
Fatigue onset | Various metrics have been described: Shift in mean (or median) frequency High/low frequency ratio (H/L ratio, with H = 150–350 Hz and L = 20–46.7 Hz) Spectral moments ratio of order five (SMR5) and fuzzy approximate entropy (fApEn) | May inform about diaphragm fatigue before a decrease in pressure-generating capacity occurs | No data and cutoff values exist Challenging to compute reliably in respiratory sEMG due to low SNR |
Magnitude of muscle activity
Estimation of force generation
Timing of muscle activity
Fatigue assessment
Applications in research and clinic
Goal | Setting | Use | References |
---|---|---|---|
Investigate mechanisms | |||
Investigate mechanisms of respiratory muscle activation | Research | For example: Muscle activation during coughing Respiratory muscle activity in health and disease Respiratory muscle activation during inspiratory loading | |
Investigate mechanisms of breathlessness | Research | Breathlessness in COPD, during exercise | |
Monitoring disease | |||
Diagnostic/Monitor disease severity | ICU/RCU/ward/home | Monitor respiratory muscle activity in pre-school children with airway symptoms | |
Predict change in clinical condition | ICU/RCU/ward/home | Monitor respiratory muscle activity to detect recovery and deterioration, need for intervention, post-discharge outcomes | |
Predict prognosis | Home | Predict long-term outcomes following AECOPD | [78] |
Response to intervention | |||
Titrate inspiratory muscle training | ICU/RCU/ward/home | Quantify respiratory muscle activation in response to different modalities and resistances | |
Response to other interventions | ICU/RCU/ward/home | For example: Response intermittent hypoxia to improve motor plasticity in ALS Response to an arithmetic task in asthmatic children Response of upper airway muscles to non-invasive ventilation | |
To optimize mechanical ventilation | |||
Titrate mechanical ventilation | ICU/RCU/ward/home | Quantification of inspiratory effort and contribution of the different respiratory muscles in order to define the optimal level of support Detect patient-ventilator asynchrony | |
Facilitate weaning from mechanical ventilation | ICU/RCU | Monitor respiratory muscle activity to detect SBT failure | [6] |