Decision Making in Emergency Critical Care

SECTION 2 - Hemodynamic Monitoring

4
Arterial Blood Pressure Monitoring

Vidya K. Rao and John E. Arbo

BACKGROUND

Arterial blood pressure (ABP) is an essential cardiovascular vital sign and monitoring parameter for all critically ill patients. ABP may be measured indirectly using an inflatable external cuff or directly by cannulation of a peripheral artery.

Indirect ABP measurement is performed noninvasively and requires the use of an external expandable cuff and a pressure gauge, known as a sphygmomanometer. The cuff is wrapped around an extremity overlying an artery and inflated to a pressure that temporarily occludes arterial blood flow. The cuff is then gradually deflated, and blood pressure is determined by auscultation of Korotkoff sounds or by an automated system that measures oscillations as blood flow resumes.

While inexpensive and easy to perform, indirect ABP measurement has limitations that make it unsuitable for critically ill patients. Auscultation is cumbersome in a busy environment and is impaired by ambient noise. The patient's body habitus as well as improper cuff size, position, or external compression can prevent an accurate measurement.13 In critically ill patients, the principal disadvantage of indirect ABP measurement is the inability to provide continuous measurement, which is useful in hemodynamic compromise or vasopressor administration. Indirect measurements also frequently fail to correlate with direct pressure monitoring, especially in times of rapidly changing or unstable hemodynamics.4,5 Finally, repetitive cycling of the blood pressure cuff can result in arm pain, limb edema, ischemia, neuropathy, and, in rare cases, compartment syndrome.68

Direct ABP monitoring, in which a catheter is inserted into a peripheral artery and continuously transduced, is the benchmark for arterial pressure measurement and is considered standard of care for most critically ill patients. An ABP catheter enables dynamic monitoring and provides continual vascular access when repetitive blood sampling is required. As discussed later in this chapter, the arterial pressure waveform also offers a wealth of diagnostic information.

GENERAL DEFINITIONS

Systolic blood pressure (SBP) is the peak pressure generated by ventricular contraction, and diastolic blood pressure (DBP) is the lowest pressure observed during ventricular filling. Pulse pressure (PP) is defined as the difference between the systolic and diastolic pressures. Mean arterial pressure (MAP) is the time-weighted average of arterial pressures in a single cardiac cycle, and represents systemic perfusion pressure. MAP is calculated using the following formula:

Noninvasive blood pressure measurement determines SBP, DBP, and MAP by comparison of oscillatory characteristics to cuff pressures, where MAP is the point of maximal oscillations during cuff deflation.9 Direct ABP measurement produces an arterial waveform that consists of a systolic peak and a diastolic trough. MAP is then determined by integrating the area under the curve.10

DIRECT BLOOD PRESSURE MONITORING

Indications

Direct ABP monitoring provides continuous, beat-to-beat arterial pressure measurement, which is essential in the management of patients who are hemodynamically unstable, have advanced cardiovascular disease or significant dysrhythmia, require vasopressor support, or whose condition necessitates targeted blood pressure control (Table 4.1). Waveform analysis can also provide significant insight into a patient's physiology, including intravascular volume status, volume responsiveness, and the presence of valvular abnormalities. As previously mentioned, this modality provides dependable vascular access and is indicated in patients with pulmonary compromise or significant acid–base derangements where frequent blood sampling is required. Peripheral arterial catheters may also be placed in patients prior to the administration of thrombolytic therapy to facilitate the collection of laboratory studies.

TABLE 4.1 Comparison of Invasive and Noninvasive Blood Pressure Monitoring in Critically Ill Patients

Site Selection

Factors that must be considered in site selection include the presence of adequate collateral circulation and patient comfort, as well as the phenomenon of distal pulse amplification that causes distal SBP measurements to be higher than central SBP, without significant differences in DBP or MAP.

The radial artery is the most commonly used vessel for ABP monitoring due to its superficial location, ease of cannulation, presence of collateral flow, and low risk of complications.11 However, due to its small caliber, this site carries the highest incidence of temporary arterial occlusion, reported to occur in over 25% of procedures performed.1113 Despite its high incidence, temporary occlusion of the artery does not appear to have serious sequelae in most cases.11 Given its peripheral location, a radial artery catheter provides a less accurate measurement of aortic pressure than do more centrally placed catheters due to distal pulse wave amplification.

The femoral artery is the second most commonly used site. The central location of this vessel allows for more accurate measurement of aortic blood pressure, particularly in patients requiring high-dose vasopressor administration, and its larger caliber mitigates the risk of temporary arterial occlusion seen with radial catheters.11 However, clinicians must be cognizant of—and monitor for—retroperitoneal hemorrhage following cannulation. Historically, there has been reluctance to use this site given its proximity to the anogenital region and the concern that it carries an increased risk of infection. However, published studies do not uniformly substantiate or refute this concern.14,15

The axillary artery has gained popularity in recent decades as it permits measurement of central pressure using a cannulation site that is considered to be in a cleaner location. This approach is more technically challenging than are others, and is often avoided due to the theoretical risk of cerebral embolic events given its proximity to the carotid artery. The incidence of major complications associated with this cannulation site was similar to that of radial and femoral catheterization.11

Complications

Arterial catheterization is generally considered to be a safe procedure, but complications can and do occur, and must be factored into site selection (Table 4.2). Risks include temporary arterial occlusion, ischemia, pseudoaneurysm, arteriovenous fistula, infection, bleeding, air embolism, and hematoma.11,16 Patients with preexisting vascular disease, arterial injury, high-dose vasopressor administration, and long-term cannulation may be at higher risk for adverse events.10 Fortunately, serious complications occur in <1% of cases.11 Use of the Allen test does not minimize complications associated with arterial artery cannulation and has been abandoned.

TABLE 4.2 Complications of Arterial Lines

Contraindications

Contraindications are generally relative, site specific, and based upon consideration of risk and benefit. Relative contraindications include significant peripheral vascular disease and Raynaud syndrome due to the associated risk of limb ischemia, and severe coagulopathy or use of thrombolytics given the risk of bleeding. Placement of intra-arterial catheters should also be avoided at sites with signs of obvious infection, burns, vascular trauma, or previous vascular surgery or grafts.17,18 Cannulation ipsilateral to arteriovenous dialysis shunts will yield false results and should be avoided.

THE MONITORING SYSTEM

Components of the Monitoring System

Data from the monitoring system must be converted into a waveform that can be visualized on the patient's monitor. Monitoring systems consist of several parts beyond the arterial cannula, including a fluid-filled system, transducer, flushing assembly, microprocessor, amplifier, and display.

  • The fluid-filled system creates a column of fluid, usually heparinized saline, between the arterial cannula and the transducer, known as hydraulic coupling. To minimize waveform distortion, the tubing must be noncompliant, as short as possible, and free of air bubbles, blood clots, and extraneous three-way stopcocks. It is imperative that the tubing be clearly labeled to avoid inadvertent intra-arterial injection of medications.
  • A flushing assembly that often contains heparinized saline pressurized to 300 mm Hg is attached to the fluid tubing to help maintain patency of the cannula. The system also allows high-pressure fluid flushes through the tubing system in order to keep it clear of clot and debris.
  • The transducer converts pressure into an electrical signal. Changes in arterial pressure are transferred via the fluid in the tubing to a flexible diaphragm contained in the transducer. Movement of the diaphragm causes an imbalance by stretching or compressing four strain gauges that are incorporated into a Wheatstone bridge circuit. The imbalance creates an electrical current.
  • Once pressure is converted into an electrical signal in the transducer, it is transmitted through an electrical cable to a microprocessor to be filtered, and then through an amplifier, after which the waveform is shown on an on-screen display.

The Physics of the Arterial Pressure Waveform

The arterial pressure waveform is composed of a fundamental wave and a series of harmonic waves. The fundamental wave frequency is equivalent to the pulse rate, and the frequencies of the harmonic waves are multiples of the fundamental frequency. Fourier analysis, the process by which the complex arterial waveform is constructed from these component waves, is performed by the microprocessor, and the arterial waveform is then amplified and visually displayed on the monitor (Fig. 4.1).19

FIGURE 4.1 The arterial pressure waveform (C) is a sum of a fundamental wave (A) and six to eight harmonic waves (B). Summation is performed by Fourier analysis. From Pittman JA, Ping JS, Mark JB. Arterial and central venous pressure monitoring. Int Anesthesiol Clin.2004;42:13–30.

The dynamic response of the ABP monitoring system is determined by resonant frequency and damping.10,20 Resonant (or natural) frequency is defined as the frequency at which a given material oscillates when disrupted. When a system is stimulated by a frequency that is close to its own resonant frequency, it oscillates and amplifies the incoming signal.9,21 Thus, if the frequencies of the fundamental or harmonic waves of an ABP waveform approach, coincide with, or overlap with the resonant frequency of the ABP monitoring system, amplification occurs and results in elevated SBP and PP measurements. The resonant frequency of the monitoring system is designed to be at least five to eight multiples above the fundamental frequency, and is determined by the physical properties of the system's components. Increasing tubing diameter while reducing tubing length, compliance, and density of the fluid in the system can increase the natural frequency of the monitoring system.

In addition to having a high resonant frequency, the ABP monitoring system must also be properly damped. Damping occurs when the energy in an oscillating system is reduced.21 While some degree of damping, termed critical damping, is essential in the monitoring system, overdamping and underdamping can result in inaccurate measurement of ABP. Overdamping may occur when the system contains excess tubing, stopcocks, occlusion, and air, and can be identified by examining the arterial waveform for a slurred upstroke, absent dicrotic notch, and loss of fine detail.9 Overdamped waves display falsely lower SBPs, falsely higher DBPs, and a narrowed PP, though MAP may still be accurate. Conversely, underdamping results in increased oscillations and therefore a falsely elevated SBP and PP. A patient's physiology can also result in underdamping; tachycardia increases the fundamental frequency given the high pulse rate. As the fundamental frequency approaches the resonant frequency of the monitoring system, oscillations are amplified and the system becomes underdamped.

The “square wave” or “fast flush” test evaluates the dynamic response of the monitoring system and helps predict signal distortion by determining the system's natural frequency and degree of damping. This test is performed by briefly opening the continuous flush valve and increasing the flow of fluid to 30 mL/h, which generates a square wave that can be seen on the patient's monitor. Once the valve is closed, the resulting oscillations on the waveform are examined. The system's natural frequency is inversely proportional to the time between successive oscillation peaks; if the oscillation cycle is shorter, the system has a higher natural frequency. The degree of damping is determined by evaluating the ratio of the amplitudes of adjacent oscillation peaks. The amplitude ratio is then referenced with a graph that contains the corresponding damping coefficient. In an underdamped system, the amplitude ratio of successive oscillation peaks will be higher, and the system will have a lower damping coefficient. Conversely, overdamped systems will have lower amplitude ratios, and an elevated damping coefficient (Fig. 4.2).

FIGURE 4.2 Square flush test. A:Optimal damping as evidenced by one to two oscillations prior to the return of the waveform. B:Underdamped: excessive oscillation and overestimation of the SBP. C:Overdamped: minimal oscillation and underestimation of the SBP.

Leveling and Zeroing

Following cannulation and connection to the pressure transducer tubing, the ABP monitoring system must be leveled and zeroed in order to provide consistent and accurate ABP measurements.

Leveling is the process of eliminating the influence of hydrostatic pressure on the measured BP. The transducer is leveled to the phlebostatic axis, defined as the intersection of the 4th intercostal space and the midaxillary line. This external location correlates to the anatomic position of the right atrium, which reflects central blood pressure. If positioned too low, the transducer will produce a deceptively high-pressure reading; if positioned too high, it will produce a deceptively low reading. Occasionally, the transducer is placed at the level of the tragus when cerebral perfusion pressure is the primary concern.

Zeroing is the process of eliminating the effects of atmospheric pressure on measured BP. To zero the system, it is opened to atmospheric pressure and set to a pressure of zero. This ensures that atmospheric pressure is the starting value.

ARTERIAL PRESSURE WAVEFORM ANALYSIS

The Arterial Waveform

The arterial waveform consists of five main elements: systolic upstroke, systolic peak, systolic decline, dicrotic notch, and the point of end diastole (Fig. 4.3).

  • The systolic upstroke, or anacrotic limb, begins with the opening of the aortic valve and appears as a rapid rise in the arterial waveform. Data regarding degree of contractility and left ventricular (LV) stroke volume may be inferred from the rate of ascent and height of the anacrotic limb.
  • The systolic peak is the highest point of the waveform and marks the SBP, or the maximum pressure generated by the left ventricle during contraction.
  • The systolic decline, or dicrotic limb, immediately follows the systolic peak and represents a decrease in blood flow out of the left ventricle.
  • The dicrotic notch is seen during the course of the dicrotic limb and represents the closure of the aortic valve and the start of diastole.
  • The point of end diastole is the lowest point of the waveform and marks the diastolic pressure.

FIGURE 4.3 Arterial pressure waveform.

Waveform Abnormalities

Close examination of the arterial line waveform can provide diagnostic clues regarding cardiac pathology, such as cardiac tamponade, aortic valvular disease, LV failure, and hypertrophic cardiomyopathy (Fig. 4.4A–D).

  • Pulsus tardusand pulsus parvus are seen in aortic stenosis due to the fixed outflow obstruction imposed on the LV by the stenotic valve. This waveform is marked by a slow systolic rise (pulsus tardus), a late peak, and diminished amplitude (pulsus parvus), often mimicking an overdamped waveform (Fig. 4.4B).
  • bisferiens pulseis seen in aortic regurgitation and is characterized by two systolic peaks secondary to the large volume of blood ejected from the LV during systole. The first peak, or percussion wave, arises from ventricular ejection. The second peak, or tidal wave, arises from a wave reflected from the peripheral circulation as well as elastic recoil of the aorta. A bisferiens pulse will also demonstrate a sharp systolic upstroke, a low diastolic pressure, and a widened PP because of a backflow of blood into the LV during diastole (Fig. 4.4C).
  • spike-and-domewaveform may be noted in cases of hypertrophic cardiomyopathy and consists of three phases. In early systole, a rapid systolic upstroke arises from the forceful LV ejection. In mid systole, SBP falls precipitously as LV outflow obstruction occurs. In late systole, a reflected wave is seen, creating a double-peaked appearance (Fig. 4.4D).22
  • Pulsus paradoxusis an inspiratory decrease in SBP in excess of 10 to 12 mm Hg. This finding may be seen in cases of cardiac tamponade or pericardial constriction (Fig. 4.4E).
  • Pulsus alternansis seen in cases of severe LV systolic dysfunction and is characterized by regular, alternating larger and smaller amplitude PP beats (Fig. 4.4F).

FIGURE 4.4 A: Normal arterial waveform. B: Pulsus parvus and pulsus tardus. C: Bisferiens pulse. D: Spike-and-dome. E: Pulsus paradoxus. F: Pulsus alternans.

CONCLUSION

Direct ABP monitoring is essential in the management of most critically ill patients. In addition to providing the dynamic BP monitoring these patients require, a nuanced appreciation of arterial BP waveforms can greatly assist the clinician in understanding a patient's underlying physiology.

LITERATURE TABLE

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