Pediatric breathing circuits

Published on 07/02/2015 by admin

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Last modified 22/04/2025

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Pediatric breathing circuits

Dawit T. Haile, MD

Anesthetic breathing circuits function to deliver O2 and anesthetic gases to patients and to eliminate CO2 from patients. They are classified according to (1) the presence or absence of unidirectional valves, (2) the presence and the position of a reservoir bag, (3) the means by which CO2 is eliminated, (4) the ability of the circuit to permit or prevent rebreathing, and (5) the efficiency of the circuit at preventing rebreathing.

Mapleson circuits

The first anesthesia breathing systems delivered NO2-O2 mixtures for dental anesthesia via a reservoir bag directly connected to an expiratory valve and a facemask. Sir Ivan Magill improved this circuit by distancing the reservoir bag from the expiratory valve and facemask with a reservoir tube to improve surgical access for facial operations. The Magill attachment, also referred to as Mapleson A, was popular for more than 50 years.

By the 1950s, several types of semiclosed circuits were used to deliver anesthetic gases. Semiclosed circuits under optimal conditions prevent rebreathing of alveolar gases. In 1954, the physicist William W. Mapleson analyzed five of these circuits and proposed optimal conditions that would prevent rebreathing. The efficiency of a nonrebreather is determined by the amount of fresh-gas flow, as well as by the positions of the inflow of fresh gas, the expiratory valve, and the reservoir bag. Mapleson labeled these circuits A, B, C, D, and E (Figure 193-1); subsequently, these circuits have been referred to as the Mapleson circuits, and Mapleson’s theoretical analyses have been verified empirically by others.

The Mapleson (A, B, C, D, and E) circuits lack unidirectional valves and a CO2 absorber. They have the advantage of reduced airflow resistance, which is ideal for use in pediatric patients. The Mapleson circuit removes CO2 by venting exhausted gas to the atmosphere, in contrast with circle systems, in which CO2 is removed by a CO2 absorber. Because Mapleson circuits lack a unidirectional valve, the fresh gas and alveolar gases mix, and significant rebreathing occurs if the fresh-gas flow is not adequate. The Mapleson A and D circuits have been analyzed most extensively, the B and the C circuits are rarely used, and the E circuit is basically a T-piece system. The D circuit is the most commonly used Mapleson circuit, and the A circuit is infrequently used but has a historical and a functional significance.

Mapleson A circuit

The Mapleson A circuit, as described earlier, comprises a reservoir tubing (corrugated tubing) separating, at one end, the fresh-gas flow passing through a reservoir bag and, at the opposite end, an adjustable pressure-limiting valve (APL valve) near the facemask. The system is the most efficient and, with spontaneous ventilation, requires less fresh-gas flow than with controlled ventilation. To explain these differences, the breathing cycle can be artificially divided into three phases: the inspiratory, the expiratory, and the expiratory-pause phase.

Immediately before the inspiratory phase of spontaneous ventilation occurs, continuous fresh gas flows into the reservoir bag and the circuit (Figure 193-2). As the patient inhales, the reservoir bag begins to empty. The lower the fresh-gas flow, or the higher the tidal volume, the emptier the reservoir bag becomes. During the expiratory phase, the reservoir bag completely fills with fresh gas, and, when the fresh-gas flow exceeds 70% of minute ventilation, enough pressure develops to vent alveolar and fresh gas through the APL valve. At the last stage of the expiratory phase, a pause occurs before the initiation of the next cycle. During the expiratory pause, fresh-gas flow further drives alveolar gas through the APL valve and virtually eliminates rebreathing.

How can a fresh gas flow that is only 70% of minute ventilation prevent rebreathing? The answer is “dead-space gas.” The gas in the reservoir tubing immediately before exhalation is dead-space gas because it is has not been exchanged within the patient’s lung and, therefore, does not contain alveolar gases. During the expiratory pause, all of the alveolar gases in the reservoir tubing and some of the dead-space gases are pushed by the fresh-gas flow and expelled through the APL valve. However, not all of the dead-space gas is expired before the next cycle. Because of this residual dead-space gas, the amount of fresh gas required to eliminate rebreathing in the Mapleson A circuit during spontaneous ventilation is less than the minute ventilation.

In contrast with spontaneous ventilation, controlled ventilation (hand ventilation) of the Mapleson A circuit empties the reservoir bag at the end of the inspiratory phase (Figure 193-3). The reservoir bag refills with a mixture of alveolar gases, fresh gas, and dead-space gases during the expiratory phase. During controlled ventilation, the expiratory pause is minimal, which increases the likelihood of alveolar gas retention in the reservoir tubing and increases the amount of alveolar gases present with the initiation of the next inspiratory phase. Among the Mapleson circuits, the Mapleson A circuit under controlled ventilation is considered to be the least efficient at preventing rebreathing; rebreathing is overcome by increasing fresh-gas flow far exceeding minute ventilation.

Mapleson D circuit

In the Mapleson D circuit, compared with the Mapleson A circuit, the positions of the APL valve and the fresh-gas-flow nipple are reversed; the fresh-gas-flow nipple is located at the patient’s end of the circuit, and the APL valve is next to the reservoir bag at the opposite end. The Mapleson D circuit is considered to be a modification of a T-piece circuit; the T-piece circuit is modified into a Mapleson D circuit by adding a reservoir bag and APL valve to the distal end of the reservoir tubing. This circuit requires slightly more fresh-gas flow to eliminate rebreathing than does the Mapleson A circuit. However, for controlled mechanical ventilation, circuit D is the most efficient of the Mapleson circuits.

During spontaneous ventilation with the Mapleson D circuit (Figure 193-4), the alveolar gases are immediately mixed with fresh-gas flow as the gases pass down the reservoir tubing and fill the reservoir bag. When the reservoir bag is filled with a mixture of alveolar and fresh gases, the mixed gas is vented out the APL valve. The first gas to exit through the APL is the dead-space gas, followed by the mixture of alveolar and fresh gases. During the expiratory pause, fresh-gas flow expels most of the alveolar mixed gas if the minute ventilation is adequate. Therefore, to prevent rebreathing, the fresh-gas flow has to be twice the minute ventilation, and the expiratory pause has to be sufficiently long to allow all of the alveolar mixed gases to be expelled.

During the expiratory phase of controlled ventilation with the Mapleson D circuit (Figure 193-5), the fresh-gas flow drives the mixed alveolar gases and dead-space gases out of the APL valve. Furthermore, during the inhalation phase, the mixed alveolar gases are pushed and expelled not only by the continuous fresh-gas flow, but also by the positive pressure of controlled ventilation. The amount of fresh-gas flow necessary to minimize rebreathing is greater than the patient’s minute ventilation.

The Bain circuit is a modification of the Mapleson D; the two circuits have the same efficiency, but the Bain circuit provides improved humidification of the inspired air and is the most compact of the Mapleson circuits. The position of the reservoir bag, APL valve, and the fresh-gas inflow in these two devices is the same except that the tube carrying fresh gas is an inner coaxial tube within the corrugated tube in the Bain circuit. The inner tube enters the circuit at the reservoir-bag end, and the fresh gas empties at the patient’s end of the circuit. The advantages of the Bain circuit over the Mapleson D include the following: (1) less equipment to interfere with the surgical field, (2) less likelihood of kinking the tracheal tube or extubating the patient because the system is lightweight, and (3) the ability to mount the Bain circuit on the anesthesia machine, allowing for expired gases to be scavenged. Gas flows and minute ventilation requirements are similar to those for the Mapleson D circuit.

Summary

The relevance of the Mapleson circuits, other than the Mapleson D and Bain circuits, is purely academic. However, the relative efficiency of rebreathing prevention and the requirement of fresh-gas flow of these circuits have been described as follows. For spontaneous ventilation, the most efficient to the least efficient is A > DE > CB. During controlled ventilation, the most efficient to the least efficient is DE > BC > A.

Most children are anesthetized with an adult circle breathing system. Infants and neonates who are too small or have sensitive mechanical ventilation requirements need a different class of modern ventilator (e.g., Siemens 300, Dräger Evita, and others). The discussion of the technology behind this class of ventilators is beyond the scope of this chapter. However, these ventilators utilize technology that can meet the oxygenation and ventilation needs of low-weight infants and neonates and that minimize lung injury more effectively than do the adult anesthesia machines.