Defibrillation was historically conceived to terminate life-threatening ventricular tachyarrhythmias with an electrical shock. Cardioversion, which consists of delivering a low-energy shock synchronized to the upstroke of the R wave of an EGM, is distinguished from defibrillation, which consists of delivering a non-synchronized, high-energy shock. In the VF zone, synchronization of the shock may not be possible because of instability of the ventricular electrograms. In practice, a Boston Science defibrillator systematically attempts to synchronize the shock to an R wave, including in the VF zone. The effects of an electrical shock vary as a function of the energy delivered. Weak energies, on the order of 1 J, delivered in the vulnerable period may induce an arrhythmia. The upper limit of vulnerability, a value correlated with the defibrillation threshold, is the lowest energy delivered in the ventricular vulnerable period that does not trigger VF. The probability of arrhythmia termination increases thereafter along an exponential curve as a function of the amplitude of the shock delivered, when synchronized with the R wave. Past a certain value, the risk of re-inducing an arrhythmia increases as well, thereby limiting the chances of therapeutic success. A shock of excessive amplitude may injure the myocardium.
The stored energy subsequently delivered by a defibrillator is expressed by the formula:
stored energy = 1/2 CV2
where C = capacitance and V = voltage;
The delivered energy can be increased by increasing either the capacitance or the voltage. Various characteristics of the shock waveform, shock vector, shock amplitude and number of shocks delivered determine the success of defibrillation and may or may not be programmable.
Shock waveform: Initially monophasic, the shock waveform of state-of-the-art defibrillators is now biphasic, lowering the defibrillation threshold. In a biphasic shock, the current is initially delivered in one direction, then, after a fixed amount of energy has been delivered, the current direction is reversed. The first phase of a biphasic shock is equivalent to that of a monophasic shock with a lesser critical mass. The second phase returns the membrane potential as close as possible to zero to prevent the re-induction of a tachycardia or of VF. The shock waveform is necessarily biphasic and is not programmable with the latest Boston Science defibrillators.
Shock vector: the programming of the shock vector depends on the number of high-voltage electrodes available. The defibrillation shock is delivered by a dedicated lead, which may be a single coil (single defibrillation electrode placed in the right ventricle) or double coil (one distal defibrillation electrode placed in the right ventricle, and one more proximal defibrillation electrode, at the level of the superior vena cava). Single-coil shocks can only be delivered between the distal coil of the RV lead and the pulse generator. Double-coil shocks can be delivered among the distal coil, the proximal coil and the pulse generator. The shock vector is programmable, and the proximal electrode in the superior vena cava can be programmed or de-programmed in a double-coil lead.
The following programmable configurations are available with a double-coil lead:
- RV coil to right atrial coil and can: this vector is also known as the V-TRIAD (double-coil). The pulse generator is an active electrode (hot can) combined with the double-coil defibrillation lead. The energy is simultaneously delivered from the distal to the proximal coil and from the distal coil to the can.
- RV coil to can: this vector also uses the pulse generator as an active electrode (hot can; single-coil). The energy is only delivered between the distal coil and the pulse generator.
- RV coil to right atrial coil: this vector, also known as “cold can”, removes the can as an active electrode. The energy is delivered between the distal and the proximal coils.
RV to can is the only working single-coil lead configuration. The 2 others, albeit programmable, should not be used. With the RV to right atrial coils configuration, no shock would be delivered. Therefore, this vector should never be used with a single-coil lead. When programmed, an alert screen appears that asks for verification that the lead is indeed a double coil.
Shock polarity: polarity can be programmed as initial or reversed. With an initial polarity, the RV coil is negative for the first phase (cathodal), while the pulse generator, the superior vena cava coil, or both are positive (anodal). This initial polarity corresponds to a cathodal shock. With a reversed polarity, the RV coil is positive for the first phase of the shock (anodal), while the pulse generator, the superior vena cava coil, or both are negative (cathodal). This reversed polarity corresponds therefore to an anodal shock.
Number of shocks: the maximum number of consecutive shocks that can be delivered in the VF zone is fixed at 8, thereby limiting the risk of an endless series of inappropriate shocks. In the VT zone, the number is limited to 6 and in the VT-1 zone to 5 shocks. Shock confirmation: ventricular shock therapy can be programmed to be non-committed or committed. The objective of a re-confirmation is to not deliver an unnecessary shock in case of spontaneous termination of the arrhythmia. The device monitors the tachyarrhythmias during and immediately after the charge of the capacitors. During that phase, it examines whether the tachyarrhythmia has spontaneously ended, and determines whether a shock is needed.
A priority of defibrillator programming is to minimize the delivery of shocks without compromising the patient’s safety. One must adopt the least aggressive and least painful treatment modality to terminate an arrhythmia. The principle behind ATP is to capture the arrhythmia and interrupt an organized VT by penetrating its propagation circuit across the ventricles. The ventricle must, consequently, be paced at a faster rate than that of the tachycardia. ATP is painless, lowers the energy consumption
and spares the batteries. It must, therefore, be favored as first-line treatment of organized ventricular rhythm disturbances, even when rapid. The efficacy of this type of therapies has been confirmed in a wide range of VT rates, up to 240 bpm. It is therefore customary, nowadays, to program a burst of ATP in the VF zone, unless it has been found ineffective or arrhythmogenic.
Several settings must be programmed to optimize the efficacy of this type of therapy:
The type of sequences: burst, ramp, sweep, ramp/sweep
The cycle length of a single burst of ATP is fixed (no change from a cycle to the next). It is the most commonly used and probably least aggressive type of sequence in clinical practice. Within a ramp, the cycle length is shortened from cycle to cycle by a programmable decremental value. In a sweep, the pacing cycle of a same sequence remains fixed (it is, therefore, a salvo). However, in a same series of salvos, the pacing cycle length decreases from one salvo to the next by a programmable interval.
In a ramp/sweep, the pacing cycle is shortened from one stimulus to the next by a programmable decremental value (ramp), and the cycle length shortens from one ramp to the next by a programmable value. This is the most aggressive type of sequence.
The number of pacing sequences
The number of programmed sequences varies as a function of the rate of the tachycardia. In a slow VT zone, a large number of sequences can be programmed in order to delay to a maximum the shock delivery for a tachycardia that does not threaten the patient’s short-term survival. It is, in fact, possible to not program an electrical shock for that slow VT zone (VT-1). For tachycardias between 150 and 200 bpm, it is usual to program 3 to 6 consecutive sequences of ATP. For the fastest VT, one or two sequences are programmed, since a risk exists of a) not ending the episode and b) delaying the shock delivery for a tachycardia that compromises the hemodynamic status and the patient’s prognosis.
Number of pulses per sequence
On average, 5 to 15 consecutive pulses are programmed in each burst. If the number of pulses is insufficient, they might not penetrate the tachycardia circuit and remain ineffective. On the other hand, if the number is excessive, they might end, and then re-induce the tachycardia. An additional pacing stimulus may be systematically added from one sequence to the other.
Coupling versus pacing cycle
The coupling cycle (delay between the last sensed and first paced ventricular event) and the pacing cycle (delay between first and the second pacing stimulus) can be programmed differently. The shorter the coupling interval, the more aggressive the therapy and the greater the risk of tachycardia acceleration. Both coupling intervals can be programmed as percentages or as fixed cycles (in ms). It seems more sensible to program in percentages in order to adapt them to the rate of the tachycardia and its variations. The percentage is calculated from the average of the 4 cycles preceding the therapy.
A rate limit can be programmed beyond which, regardless of the programming, the device will not pace. If, during a ramp, for example, the minimum interval has been reached, the following cycles will be paced at that minimum coupling cycle length without further decrement.
Longest duration of ATP
This duration is the time after which the ATP sequences are interrupted in favor of the delivery of an electrical shock. This feature was designed to prevent a delay in the delivery of the first shock by the delivery of too many sequences of ATP.
Pacing pulse amplitude
The chances of reliable ventricular capture can be increased by programming the amplitude and duration of the ATP pulses independently (nominal value = 5 V/1.0 ms).
From an initially empiric programming, the pulses are subsequently adapted according to:
- the various arrhythmias recorded by the device and analyzed during the patient’s follow-up,
- the efficacy (termination of the episode) / adverse effect (acceleration of the arrhythmia) ratio of a
type of pacing sequence.
Antitachycardia pacing in the VF zone: Quick Convert™
ATP has proven its efficacy in the termination of even fast ventricular tachyarrhythmias. With the most recent devices, a burst of ATP can be programmed in the VF zone, using the Quick Convert function.
The characteristics of Quick Convert are not programmable:
- single burst
- 8 stimuli
- coupling cycle = 88% of the tachycardia cycle length
- pacing cycle = 88% of the tachycardia cycle length
- shortest paced cycle length = 220 ms
The ventricular rate must be <250 bpm (based on an average of the 4 preceding cycles) for a burst to be delivered. The burst is only used as a first attempt at treatment of an episode. Once the burst has been delivered, the device analyses the rhythm: if the arrhythmia persists, the capacitors begin to charge; if the arrhythmia has ended, the charge is withheld.
The device applies the following criteria to examine the efficacy of the burst:
- the first cycle after the burst is not counted. If a 2 sec asystole is observed (no sensed ventricular event), shock therapy is diverted (no charge) and the device switches to redetection.
- if 2 out of 3 intervals after the burst are faster than the lowest rate threshold (lowest programmed limit of the detection zone), the arrhythmia is considered as persistent and the charge begins.
- if 2 out of 3 intervals are slow, shock therapy is diverted (no charge) and the device switches to redetection.
After an unsuccessful burst, the charge onset marker appears on the tracing 300 ms after the charge has effectively started. The charge begins on the second fast cycle, though the marker may sometimes not be visible before the third.
Quick Convert enables the painless termination of a considerable proportion of organized VT episodes detected in the VF zone. This algorithm also prevents the charge of the capacitors, preventing thereby a premature depletion of the batteries. However, if the burst is unsuccessful, the charge of the capacitors is delayed by 1.5 to 2.5 sec compared to the usual function (shock as first-line therapy in the VF zone).