Ventilation

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Ventilation

Ventilation is the process of moving each breath, the tidal volume (VT), in and out of the lungs. During tidal ventilation, fresh atmospheric air mixes with and replaces some of the air already in the lungs. Each exhalation removes some of the carbon dioxide (CO2) the blood brings to the alveoli. Each inhalation replenishes the oxygen (O2) the blood removes from the alveoli. Because not all the inspired VT reaches the alveoli, only a portion of it participates in the gas exchange that occurs between blood and alveolar air, a process called external respiration. The depth and frequency of tidal breathing (i.e., the ventilatory pattern) greatly affects this gas exchange. Respiratory therapists and other health care clinicians must clearly understand factors affecting ventilation and respiration to assess the benefits and hazards of treatment options.

Partial Pressures of Respiratory Gases

The measurement of respiratory gas pressures must be understood to comprehend the function of the lung as a gas-exchange organ. Air is a gas mixture of mostly nitrogen (N2) and O2, with traces of argon, CO2, and other gases (Figure 4-1, A). The total combined pressure exerted by these atmospheric gases, the barometric pressure (PB), can be measured by a mercury (Hg) barometer, as shown in Figure 4-1, B. At sea level, atmospheric pressure exerts a force equal to the weight of a mercury column 760 mm high. By convention, standard atmospheric pressure at sea level is expressed simply as the height of the mercury column it supports, or 760 mm Hg. (The term torr is equivalent to mm Hg. In this book mm Hg is used.)

According to Dalton’s law, the pressure of each gas that makes up air exerts a partial pressure proportional to its fractional concentration in air. The partial pressure of any gas (Pgas) in air is equal to its fractional concentration (Fg) multiplied by total atmospheric pressure: PB (Pgas = Fg × PB).

Because oxygen constitutes 20.93% of dry atmospheric air, its partial pressure (PO2) at sea level is calculated as follows:

PO2=0.2093×760mmHg=159mmHg

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The partial pressure of carbon dioxide (PCO2) is similarly calculated:

PCO2=0.0003×760mmHg=0.228mmHg

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In physiological calculations, the PCO2 of inspired air is considered to be 0 mm Hg.

The act of inspiring heats air to body temperature (37° C) and saturates it with water vapor (100% relative humidity [RH]). The partial pressure of water vapor (PH2O) is determined by only temperature and RH. Because the body maintains lung temperature and RH at 37° C and 100% RH, the PH2O of gas in the lung is constant; under body temperature and humidity conditions, PH2O is always 47 mm Hg. At sea level, the total pressure of all gases in the lung, including water vapor, is 760 mm Hg. Water vapor accounts for 47 mm Hg, which means the rest of the atmospheric gases account for the remaining 713 mm Hg. Therefore, 47 mm Hg first must be subtracted from PB to calculate Pgas in the lung or blood. In the lung’s airways, PO2 is calculated as follows:

PO2=0.2093×(76047)mmHg=149mmHg

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Classification of Ventilation

Minute or Total Ventilation

Minute ventilation (V.imageE) is defined as the volume of air either entering or leaving the lung each minute; that is, the volume of air inhaled each minute must be equal to the volume exhaled each minute. In clinical practice, V.imageE is usually measured by adding together the exhaled tidal volumes obtained over 1 minute—hence the subscript E. Theoretically, the same result would be obtained by summing the inhaled tidal volumes over 1 minute, but exhaled volumes are easier to measure clinically. Regardless of the measuring method, V.imageE is the product of VT and breathing frequency (f) per minute (V.imageE = VT × f). If VT is 500 mL and breathing frequency is 12 breaths per minute, V.imageE is calculated as follows:

V.E=500mL×12/min

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V.E=6000mL/minor6.0L/min

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V.imageE is easy to measure but not particularly useful in evaluating the amount of ventilation that participates in gas exchange (respiration) at the alveolar level. Not all the V.imageE reaches the alveoli because the last part of each inspiration (about one third of the VT) stays in the conducting airways and is eliminated with the next expiration (Figure 4-2). Likewise, the first one third of the next inspired VT is reinspired exhaled air; it consists of the air left in the conducting airways from the last exhalation. Thus, only part of the V.imageE ventilates the alveoli; this part is called alveolar ventilation (V.imageA). The remaining part ventilates conducting airways, which is called anatomical dead space ventilation (V.imageDanat). V.imageE can be expressed in terms of its components (V.E=V.Danat+V.Aimage). This equation can be rearranged to solve for any of its components (V.A=V.EV.Danatimage or V.Danat=V.EV.Aimage). A single VT can be similarly expressed (VT = VDanat + VA), where VDanat is anatomical dead space volume and VA is alveolar volume.

Dead Space Ventilation

Anatomical Dead Space

The conducting airways from the mouth and nose down to and including terminal bronchioles constitute anatomical dead space (VDanat). Ventilation of these airways is necessary to move gas to and from the alveoli, but no gas exchange occurs between blood and air across their walls. The fresh gas filling the conducting airways at the end of inspiration (see Figure 4-2, left) is exhaled and is sometimes called “wasted” ventilation because it takes no part in respiration. The term wasted ventilation is synonymous with dead space ventilation. Dead space is defined as airspaces that are ventilated but do not exchange gases with the pulmonary circulation.

The volume in the conducting airways (VDanat) does not change unless surgery removes part of a lung or an artificial airway (endotracheal or tracheostomy tube) bypasses the upper airway dead space. Anatomical dead space increases slightly during a deep inspiration and with administration of drugs that relax smooth airway muscle because these factors increase the airway diameter. Diseases characterized by hyperinflation of the lungs (e.g., emphysema) increase VDanat for the same reason. For clinical monitoring purposes, VDanat is considered to be constant.

Gas Composition of Anatomical Dead Space

The composition of VDanat gas is different at the end of expiration than at the end of inspiration (Figure 4-3). An inspired VT of 500 mL completely flushes the normal 150 mL of VDanat with atmospheric air, leaving behind a PCO2 of 0 mm Hg and a PO2 of 149 mm Hg (see Figure 4-3, left). Dead space gas is identical in composition to inspired air except that it is 100% humidified. After the 500 mL of VT is completely exhaled, the 150 mL of VDanat (see Figure 4-3, right) is wholly occupied by gas that came from the alveoli. The humidified atmospheric air that occupied the dead space at end-inspiration was exhaled ahead of the alveolar gas (i.e., this gas was wasted because it did not participate in respiration). At end-tidal expiration, dead space gas is identical in composition to the average alveolar gas composition. Under normal circumstances, end-tidal expiratory gas is assumed to be identical in composition to alveolar gas.

The alveolar gas residing in the dead space is reinspired with the next breath. Therefore, the first 150 mL of the inspired VT does not change the alveolar gas composition.

The exhaled VT is a mixture of dead space gas (identical to inspired gas—containing no CO2) and alveolar gas (which contains CO2). The PCO2 of mixed exhaled gas is lower than alveolar PCO2 (PACO2) because dead space gas free of CO2 is a component of exhaled gas. This fact is helpful in understanding the calculation of the dead space-to-tidal volume ratio (VD/VT) later in this chapter.

Measuring Anatomical Dead Space

VDanat is related to lung size; in normal adults, anatomical dead space is approximately 1 mL per pound of ideal body weight.1 The Fowler technique provides a more precise measurement of VDanat (Figure 4-4).2 In the Fowler technique, the subject first exhales maximally to residual volume (RV), then takes a maximal inhalation of 100% O2 to total lung capacity, then exhales maximally to RV again. This technique is based on the fact that air is a mixture of N2 and O2. An N2 analyzer is used to measure continuously the exhaled N2 concentration at the mouth after the single maximal inspiration of 100% O2. N2 concentration measured at the mouth decreases abruptly to 0 during the 100% O2 inspiration (see Figure 4-4). At the end of inspiration, VDanat contains pure O2, which is the first gas to be exhaled. This means that N2 concentration remains at 0% for the first part of the expiration.

As expiration proceeds, alveolar gas (which still contains some N2) moves up into the conducting airways, and dead space N2% gradually increases to alveolar levels—note the S-shaped curve in Figure 4-4. The increase in N2% would be sharp and abrupt if dead space and alveolar gas were completely separated, as illustrated by the hypothetical square front in Figure 4-5, A. If this were the case, N2% would remain at 0% until all dead space gas was expired, and then it would abruptly increase to alveolar levels when alveolar gas suddenly appeared, as shown by the theoretical thin, solid vertical line in Figure 4-4. VDanat would simply be the volume exhaled to the sharp increase in N2%. However, alveolar gas moves through conducting airways in a conical rather than square front (see Figure 4-5, B), mixing with dead space gas. This movement makes it difficult to detect the exact point at which only the VDanat has been expired. It is necessary to construct a line representing the theoretical square front that would be seen if all N2-free dead space gas were expired first, followed by only N2-containing alveolar gas. The hypothetical square front is constructed by placing a vertical line (see Figure 4-4) such that area A equals area B (i.e., in effect, the vertical line averages alveolar and dead space gas compositions). The dead space volume is the volume expired up to the hypothetically constructed square front.

Alveolar Ventilation

V.imageA is the amount of gas entering or leaving the alveoli per minute. It is the effective portion of the V.imageE in the sense that only V.imageA takes part in respiration. As shown previously, if V.imageD and V.imageE are known, V.imageA is easily calculated (V.A=V.EV.Dimage).

All CO2 in exhaled gas comes from ventilated alveoli that have blood flowing through their capillaries. The source of this CO2 is tissue metabolism. Normal aerobic metabolism produces CO2, which is carried by venous blood to the lungs (see Figure 4-3). The mixed venous PCO2 (Pv¯imageCO2) approaching the alveoli is several millimeters of mercury higher than PACO2. Thus, CO2 diffuses into the alveoli.

Inspiration brings fresh CO2-free gas into the alveoli, and expiration removes a portion of the CO2-rich alveolar gas (see Figure 4-3). The balance between metabolic CO2 production per minute (V.imageCO2) and its rate of elimination (V.imageA) determines the PCO2 of alveolar gas and the PCO2 of the blood leaving the lung.

Hyperventilation and Hypoventilation

If V.imageA momentarily removes more CO2 per minute than is metabolically produced, alveolar and blood PCO2 decrease, and a state of hyperventilation exists. Similarly, if V.imageA momentarily removes less CO2 than the body produces, alveolar and blood PCO2 increase, and a state of hypoventilation exists. Normally, alveolar gas and blood PCO2 values equilibrate as blood flows past alveoli and enters the left ventricle. As Figure 4-3 shows, arterial blood arising from the left ventricle has the same PCO2 as the alveoli (PACO2 = PaCO2).

V.imageA determines PaCO2 because it controls PACO2. The PaCO2 obtained clinically through arterial blood gas analysis is the definitive indicator of V.imageA. Hyperventilation and hypoventilation are defined by V.imageA relative to CO2 production, a relationship that can be known only by measuring PaCO2. If PaCO2 is above normal (hypercapnia), hypoventilation exists; if PaCO2 is below normal (hypocapnia), hyperventilation exists. The presence of hyperventilation or hypoventilation cannot be reliably determined by observing only the respiratory rate or VT depth.

Alveolar Ventilation and PACO2

PACO2 is inversely related to PACO2×V.A=KimageV.imageA; if V.imageA is reduced by half, PACO2 doubles. If V.imageA doubles, PACO2 (and PaCO2) is reduced by half. For example, if a V.imageA of 5 L per minute produces a PACO2 of 40 mm Hg, a V.imageA of 10 L per minute produces a PACO2 of 20 mm Hg. Similarly, a V.imageA of 2.5 L per minute produces a PACO2 of 80 mm Hg. The V.imageA equation illustrates this relationship ().3 In this equation, K is a constant. (See Appendix III for the derivation of this equation.) This equation is based on the assumption that during a steady state of blood flow and ventilation, CO2 production (V.imageCO2) is constant and equal to CO2 elimination. Normally, PACO2 and PaCO2 have almost identical values; as a rule, V.imageA has the same relationship with PaCO2 as it has with PACO2. Figure 4-6 illustrates the inverse relationship between PaCO2 and V.imageA

PCO2 Equation

Because dead space does not participate in gas exchange, all CO2 in exhaled gas comes from the alveoli. The amount of CO2 the lungs exhale each minute (V.imageCO2) equals the V.imageA multiplied by the concentration of CO2 in the alveoli. This is shown as follows:

In this equation, FACO2 is the fractional concentration of CO2 in the alveoli. The PACO2 can be determined by multiplying FACO2 by the total alveolar gas pressure. Therefore, equation 1 can be rewritten as follows:

In this equation, K is a constant that reconciles the different measurement units; V.imageCO2 is measured in milliliters per minute,

V.imageA is measured in liters per minute, and PACO2 is measured in millimeters of mercury (see Appendix III for the derivation of K). Equation 2 can be solved for PACO2 as follows:

In this equation, 1/K is equal to 0.863. The classic PCO2 equation is written as follows:

Because PACO2 is usually equal to PaCO2 in the absence of lung disease, PaCO2 can be substituted for PACO2. This is shown as follows:

Equation 5 means that the balance between the rate of CO2 elimination (V.imageA) and the rate of CO2 production (V.imageCO2) determines the PaCO2. For example, under normal resting conditions, the body produces about 200 mL of CO2 each minute, and alveolar ventilation is about 4 L per minute; using equation 5, PaCO2 is calculated to be about 43 mm Hg. If V.imageA decreases to 3 L per minute while V.imageCO2 stays the same, PaCO2, as calculated with equation 5, would increase to about 58 mm Hg, indicating the presence of hypoventilation. If instead the metabolic rate increases, increasing CO2 production to 300 mL per minute, but V.imageA stays at 4 L per minute, PaCO2 increases to 65 mm Hg, again indicating hypoventilation. In the latter example, the lungs fail to increase V.imageA to meet the increased need for CO2 elimination. (See Appendix III for the complete derivation of equation 5 and the 0.863 factor.) Equation 5 also can be solved for V.imageA; if the PaCO2 and V.imageCO2 are known, V.imageA can be calculated as follows:

Modern CO2 measuring devices called capnometers make it feasible to measure V.imageCO2 in the clinical setting. This information, coupled with arterial blood PaCO2 analysis, allows V.imageA to be precisely quantified.

Ratio of Dead Space to Tidal Volume

V.imageA can be calculated if the fraction of VT that is dead space (VD/VT) is known. Normally, about 30% to 40% of the inspired VT remains in conducting airways, never reaching alveoli (see Figure 4-2, left), which means V.imageD constitutes about 30% to 40% of V.imageE.3 It follows that about 60% to 70% of the V.imageE is V.imageA. Shallow tidal volumes increase VD/VT because conducting airway volume (VDanat) remains constant (see Figure 4-2, right). Deep breaths decrease VD/VT for the same reason, causing a larger percentage of the inspired volume to reach the alveoli.

With the basic relationship (VT = VD + VA), VA can be expressed in terms of VD/VT and VT. This is shown as follows:

VA=VT(1[VD/VT])

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This formula is useful if VD is unknown but VD/VT is known. For example, if a normal adult weighing 150 lb has a VT of 500 mL and VD/VT equals 0.33, 33% of the VT is dead space; the remaining 67% of the VT must be VA. This is shown as follows:

VA=500(10.33)

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VA=500(0.67)

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VA=335mL

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The VD/VT can be clinically calculated if the mixed exhaled carbon dioxide (PE¯CO2image) and PaCO2 partial pressures are known. The physiological dead space equation, known as the Bohr equation, allows the VD/VT to be calculated in the following manner:

VD/VT=PaCO2PE¯CO2PaCO2

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In this equation, PE¯CO2image is the mean carbon dioxide pressure of mixed-expired gas (dead space plus alveolar gas). (See Appendix III for the derivation of the Bohr equation.)

The Bohr equation is based on the premise that all CO2 in mixed-expired gas originates from the alveoli and not the dead space. Figure 4-7 illustrates this point; the lightly shaded blocks represent CO2-free inspired air, and the darkly shaded blocks represent CO2-containing alveolar gas. The CO2 in exhaled gas (two dark blocks) comes from the alveoli; dead space gas, which contains no CO2 (one light block), makes up the rest of the exhaled volume.

PE¯CO2image is always less than PACO2 because the exhaled VT consists of VDanat gas, which has a PCO2 of 0 mm Hg, mixed with alveolar gas (Figure 4-8). The degree to which VDanat gas reduces the PCO2 of mixed expired gas is reflected by the size of the difference between PACO2 and PE¯CO2image. This difference is proportional (image) to VDanat (see Figure 4-8), shown as follows:

VDanat(PACO2PE¯CO2)

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In Figure 4-8, two thirds of the exhaled VT originates from alveoli (PACO2 of 40 mm Hg), and one third originates from VDanat (PCO2 of 0), yielding a mixed-expired PCO2 of 26.7 mm Hg. The Bohr equation confirms that VD/VT is 0.33 (i.e., that VDanat is one third of VT). The PACO2PE¯CO2image difference in the numerator of the Bohr equation reflects only the presence of VDanat. It does not accurately reflect the presence of VDA. As illustrated in Figure 4-9, if some alveoli lose their blood flow, the PCO2 values hypothetically decrease to 0, causing average PACO2 to decrease also. (Average PACO2 is measured through an analysis of the gas stream at end-expiration.) Mixed-expired gas in Figure 4-9 contains anatomical plus alveolar dead space gas, causing PE¯CO2image to decrease to 13.3 mm Hg. (Compare Figures 4-8 and 4-9.) If alveolar dead space is present, and the PACO2PE¯CO2image difference is improperly used in the numerator of the Bohr equation, the calculated VD/VT is 0.34 (see Figure 4-9), essentially the same as in Figure 4-8, where no VDA is present. However, if the PACO2PE¯CO2image difference is used in the Bohr equation, the physiological, or total, dead space can be calculated. This form of the Bohr equation takes into account both VDA and VDanat4 The term (PACO2PE¯CO2image) should be used with the Bohr equation in the clinical setting because the size of this difference is directly proportional to the total VD. This is shown as follows:

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Figure 4-9 Physiological dead space and VD/VT measurement. If the formula from Figure 4-8 is used when alveolar dead space is present, VD/VT is underestimated. The PACO2PE¯CO2image difference is directly proportional to physiological dead space (VDanat plusVDA).

VD(PaCO2PE¯CO2)

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Changes in alveolar blood flow commonly occur in critically ill patients and are of great clinical interest. Conducting airway volume is not subject to periodic changes. Therefore, measuring VDanat is not of great clinical importance. Rapid breathing increases VDanat ventilation simply because it increases the number of times the VT moves through the conducting airways each minute. Clinical physical assessment (counting the respiratory rate) easily detects this condition. However, placing a tracheostomy tube in the trachea below the larynx reduces the VDanat because it bypasses all upper airways. Thus, for a given VT, the alveoli would receive more ventilation than if the patient breathed normally through the upper airways. Endotracheal intubation also reduces VDanat because the volume of the tube is much less than the volume of the upper airways.

Figure 4-9 illustrates the Douglas bag method for clinically measuring the mixed-expired gas in determining VD/VT. The person’s expired gas is collected over several minutes in a large, previously airless balloon (Douglas bag). An arterial blood sample is obtained at the same time. Mixed-expired and PaCO2 values are used in the Bohr dead space equation. (The Douglas bag is no longer used clinically, but it is used in this example to illustrate the concept.)

A capnometer is a device used in the clinical setting to analyze exhaled CO2. These instruments respond instantaneously to PCO2 changes. Capnography refers to the PCO2 changes of exhaled tidal volumes graphically displayed as a waveform (capnogram). A capnogram allows the PCO2 to be identified at the end of a tidal exhalation (PETCO2), which corresponds to average PACO2 (PACO2 = PETCO2). (PETCO2 reflects alveolar gas composition and is not equal to mixed expired PCO2, which reflects the composition of a mixture of dead space and alveolar gases; i.e., PETCO2PE¯CO2image.) A microprocessor can determine the average PCO2 over the entire exhaled VT (PE¯CO2image).

Successive measurements over time are useful for following trends and assessing the effects of therapeutic interventions on pulmonary blood flow. VD/VT is a measure of ventilatory efficiency. A high VD/VT means much of the V.imageE is wasted in ventilating nonperfused alveoli, requiring high-energy expenditure to accomplish a relatively small amount of V.imageA

Clinical Focus 4-3   Causes of and Physiological Response to Increased Dead Space-to-Tidal Volume Ratio

A 55-year-old woman is admitted to the hospital in obvious respiratory distress. Her increased rate and depth of breathing have increased her minute ventilation to 15 L per minute. Arterial blood gases show a normal PaCO2 of 40 mm Hg. It seems odd that this woman, with a minute ventilation this great, has a normal PaCO2. What is the explanation for this?

Discussion

A normal PaCO2 associated with high minute ventilation indicates that much of this patient’s ventilation is not in contact with blood flow. Dead space is the term used to describe alveoli that have normal ventilation but no blood flow (perfusion) through their capillaries. Any factor that decreases perfusion increases alveolar dead space. Increased alveolar dead space decreases alveolar ventilation if minute ventilation stays the same. Pulmonary embolism (obstruction of pulmonary vessels by blood clots) and shock (decreased cardiac output and low perfusion) are conditions that cause increased alveolar dead space. VD/VT increases as a larger percentage of the VT becomes dead space. In conditions producing dead space, the body tries to maintain a normal PaCO2 by increasing the minute ventilation. This increased minute ventilation does not mean alveolar ventilation increases because much of the minute ventilation is directed toward dead space units. A physiological consequence of increased dead space is the increased work of breathing required to maintain a normal PaCO2.

Patients with obstructive lung disease have impaired ventilatory capacity and may be unable to accommodate the increased demand for minute ventilation created by conditions that produce dead space. Increased dead space may precipitate ventilatory failure in these patients.

Ventilatory Pattern, Dead Space, and Alveolar Ventilation

The rate and depth of ventilation affect V.imageA and VD/VT. Figure 4-10 illustrates that V.imageE is an unreliable indicator of V.imageA. In parts A, B, and C, VDanat and V.imageE are identical. (V.imageE is 8000 mL per minute and VDanat is 150 mL in each instance.) Figure 4-10, B, represents a normal VT and respiratory rate. V.imageD is the product of respiratory frequency and VD (V.imageD = VD × f).

In Figure 4-10, B, V.imageD equals 16 multiplied by 150, or 2400 mL per minute. The V.imageA of 5600 mL per minute is equal to V.imageEV.imageD (8000 − 2400 = 5600 mL/min). For the following discussion, it is assumed that this V.imageA maintains a normal PaCO2 of 40 mm Hg, representing neither hyperventilation nor hypoventilation. Figure 4-10, A, illustrates the inefficiency of rapid (tachypnea), shallow (hypopnea) breathing. The lung still achieves a V.imageE of 8000 mL per minute, but V.imageD necessarily increases (V.imageD = 32 × 150 = 4800 mL/min, compared with a V.imageD of 2400 mL per minute in B). This leaves only 3200 mL per minute for V.imageA compared with 5600 mL per minute in B. VD/VT increases also; in Figure 4-10, B, it is 150/500, which equals 0.3, and it is 150/250 or equal to 0.6 in part A. In Figure 4-10, B, 70% of the V.imageE is involved in alveolar gas exchange, whereas only 40% is similarly involved in part A. Rapid, shallow breathing is a common signal of respiratory distress and possible ventilatory failure.

Figure 4-10, C, illustrates a slow (bradypnea), deep (hyperpnea) breathing pattern that also achieves a V.imageE of 8000 mL per minute. Because VDanat is constant, all the additional VT enters alveoli, increasing V.imageA. V.imageD is only 8 × 150, which equals 1200 mL per minute, leaving 6800 mL per minute for V.imageA. VD/VT is 150/1000 or equal to 0.15, meaning 85% of V.imageE participates in gas exchange. Slow, deep breathing is the most efficient ventilatory pattern in terms of the fraction of V.imageE received by alveoli.

Clinical Focus 4-5   High-Frequency Ventilation: Tidal Volumes Smaller than Anatomical Dead Space Volume

It is possible to ventilate the lung adequately with tidal volumes smaller than the anatomical dead space volume if the respiratory rate is very high. Mechanical high-frequency ventilation (HFV) is most often used on premature newborn infants with underdeveloped lungs that do not expand properly (respiratory distress syndrome of the newborn). Less often, HFV is used on adults with severe acute lung injury. The extremely small tidal volumes place little mechanical stress on the lungs because they do not stretch the underdeveloped or injured alveoli very much. Two types of HFV are high-frequency jet ventilation (HFJV) and high-frequency oscillatory ventilation (HFOV). HFJV pulses small jets of gas very rapidly into the trachea through a small tube inside of an endotracheal tube. HFOV uses a mechanism such as a flexible diaphragm to vibrate or oscillate gas back and forth rapidly in the airways. In either type of HFV, there are no distinguishable inspiratory and expiratory phases or measurable tidal volumes. HFJV cycling rates may be 5 pulses per second (5 Hz) in adults to 7 Hz in infants (300 to 420 “breaths” per minute). HFOV uses even higher cycling frequencies, up to 15 Hz (900 cycles per minute) in infants. In HFV, the conventional relationships (discussed in this chapter) among tidal volume, frequency, dead space, and alveolar ventilation become meaningless. In HFV, alveolar ventilation and gas exchange do not occur via bulk gas flow in and out of the lungs; rather, they occur through complex gas mixing and diffusion mechanisms. As small bursts of gas are pulsed or oscillated through the airways, flow turbulence and eddy currents help mix gas and enhance diffusion. In this process, gas moves in and out of the airway at the same time. (One can appreciate this two-directional flow phenomenon by blowing air through a straw inserted halfway into a test tube.) In HFV, inspiratory gas pulses down the center of the airway, while expiratory gas streams in the opposite direction along the airway walls, a process known as coaxial flow. Whatever the physical principles involved, HFV can maintain adequate gas exchange with extremely small volumes and rapid breathing rates.