Clinical Concepts and Commentary
Target-Controlled Drug Delivery: Progress toward an Intravenous “Vaporizer” and Automated Anesthetic Administration
Egan, Talmage D. M.D.
Section Editor(s): Weiskopf, Richard B. M.D., Editor
CURRENTLY, anesthesiologists routinely use a variety of sophisticated devices for the delivery of IV drugs. The gravity-driven infusion systems in widespread use just a few years ago are primitive compared with the convenience, accuracy, and precision provided by today's calculator pumps. However, although modern infusion systems are remarkably advanced, they still fall short of the convenience and theoretical appeal associated with the delivery of inhaled anesthetics by an agent-specific vaporizer. Emulation of the clinical convenience and pharmacokinetic-dynamic control provided by vaporizers is perhaps the ultimate goal in the development of infusion devices for IV anesthetics.
The aim of this brief review is to contrast IV versus inhaled anesthetic delivery systems, develop the concept of the computer-controlled infusion pump as an “intravenous vaporizer,” and survey the current state of the art in computer-controlled IV drug delivery.
Intravenous versus Volatile Delivery Systems
Drug Delivery via a Vaporizer
Administering volatile anesthetic through the lung via a calibrated vaporizer affords several fundamental advantages that are a function of gaining access to the circulation via the lung. Because of the equilibration between the alveolar and pulmonary capillary partial pressures, the partial pressure of an inhaled anesthetic in the blood and at the site of drug action approaches the setting on the vaporizer as anesthetic administration continues. This enables impressively accurate drug administration; the clinician can set a partial pressure above which the blood concentration will not increase. Moreover, the expired concentration target can be measured with respiratory gas analysis, providing pharmacokinetic confirmation. Finally, the clinical meaning of the measured concentration is well described and understood in terms of minimum alveolar concentration (MAC), providing an element of pharmacodynamic control. Clinicians know and understand MAC; in conducting an anesthetic they think in terms of delivering the appropriate MAC fraction (or multiple) for a given patient, operation, and anesthetic technique.
Drug Delivery via a Calculator Pump
In contrast, when access to the circulation is gained directly, there is nothing to prevent the continual uptake of drug. Thus, without the aid of a computer model, the infusion rate of an IV anesthetic does not reveal much about the resulting concentration in the blood, preventing concentration-targeted administration. Furthermore, there is no capability to measure the concentration of IV anesthetics in real time, preventing pharmacokinetic confirmation equivalent to that when using a vaporizer for inhaled anesthetics. Finally, even if concentrations of IV drugs were measurable in the clinical setting, the meaning of a given concentration is not widely understood; that is, a thoroughly researched and widely appreciated analog of MAC for IV drugs is not yet fully developed. Clinicians in some parts of the world (most notably the United States and Canada) are not accustomed to thinking in terms of the appropriate target concentration of IV drug instead of an appropriate infusion rate. Thus, current calculator pumps, although accurate and sophisticated, fall short of the theoretical appeal and practical convenience associated with the delivery of volatile anesthetics via the lung.
Computer-controlled Drug Delivery as an Intravenous Vaporizer
Target-controlled infusion (TCI) systems deliver IV drugs according to the drug's pharmacokinetic behavior using an infusion pump controlled by a computer. As illustrated in figure 1
, based on the drug's typical pharmacokinetic behavior (as characterized by a population pharmacokinetic model constructed from a clinical pharmacology study), the computer pump control algorithm calculates the infusion rate that is necessary to achieve a user-designated drug concentration (the “target”) in the bloodstream. After calculating the infusion rate, the computer directs the infusion pump to administer the appropriate dosage of drug. Because the drug accumulates in the body, the computer frequently recalculates the appropriate dosage based on the computer's pharmacokinetic simulation of the current drug concentration (Cpredicted
) in the bloodstream. In this way, the computer's prediction of the current drug concentration serves as continuous input to the computer's pump control algorithm.
TCI pumps make progress toward the concept of a “vaporizer” for IV drugs because they address the fundamental limitation associated with delivering drugs directly into the circulation. 1
Constant-rate infusions result in continuous drug uptake. TCI pumps, in contrast, gradually decrease the rate of infusion based on the drug's pharmacokinetics.
Although TCI systems use complex mathematical models to compute the drug dosage, 2
in general terms the dosage regimen is patterned after the Bolus-Elimination-Transfer (BET) method first described by KrugerThiemer. 3,4
This method relies on an initial bolus (the B
of BET) to achieve the target concentration, a continuous infusion to replace drug that has been eliminated (the E
of BET) and an exponentially decreasing infusion to replace the drug that is transferred (the T
of BET) to peripheral tissues. The infusion rates are updated frequently (as often as every 10 s), depending on the predictions of the pharmacokinetic model and any changes in the target concentration set by the user.
A unique feature of TCI systems is that they can account for demographic, physiologic, or disease state covariates (i.e., patient characteristics) that alter drug disposition. For example, if a given pharmacokinetic study has shown that age, body weight, or gender alter drug clearance or distribution, this influence is incorporated into the pharmacokinetic model used by the TCI system. The influence, if known, of physiologic covariates such as kidney or hepatic function and disease states such as congestive heart failure can also be incorporated into the models. When a covariate alters an individual pharmacokinetic parameter, it is impossible to make adjustments for this kinetic alteration fully when using calculator pumps (i.e., the covariate influences the dosage scheme in a very complex way); this is a distinct advantage of TCI systems.
Delivery of drug via a computer-controlled infusion pump requires a different knowledge base of the physician. Rather than setting an infusion rate based on clinical experience and literature recommendations, the anesthesiologist using a TCI system designates a target concentration and the computer calculates the infusion rates necessary to achieve the concentration over time. Successful use of a computer-controlled infusion pump thus requires that the user think in terms of, and specify, the appropriate therapeutic concentration rather than the appropriate infusion rate.
In setting the target, the anesthesiologist relies on three sources of information, as shown in figure 1
. The initial target is set on the basis of knowledge of the drug's therapeutic windows in the context of a specific patient (e.g.
, patient demographic features and medical condition) and a procedure (e.g.
, type and level of noxious stimulation). Subsequent adjustments to the target are made on the basis of patient response and the predicted drug concentration.
Drug delivery by a computer-controlled pump according to a pharmacokinetic model has been referred to by a variety of names in the anesthesia literature. Known variously as computer-controlled infusion pump (CCIP), computer-assisted continuous infusion (CACI), target-controlled infusion (TCI), computer assisted titration of IV anesthesia (CATIA), and model-based drug delivery, all of these methods of computer-controlled delivery are “open-loop,” in that no feedback from the patient is automatically considered by the pump infusion-control mechanism. The computer prediction of the current drug concentration is the only feedback evaluated by the pump. The anesthesiologist must assess the adequacy of patient response and change the target concentration as necessary. In recent years, TCI has emerged as the consensus, preferred nomenclature for open-loop devices. 5
“Closed-loop” computer-controlled drug delivery is fundamentally different in that the computer controller evaluates a real-time measure of drug effect such as a peripheral nerve stimulator for muscle relaxants or the processed electroencephalogram for hypnotics and adjusts drug delivery on the basis of that measure (i.e., the feedback signal comes from a monitor). For both open- and closed-loop infusers, the computer's control algorithm considers differences between the target and the feedback signal and generates a “control signal.” This control signal alters the pump behavior to achieve the desired target.
TCI systems report a predicted concentration for the drug of interest. Because the TCI system predicts the concentration on the basis of the drug's typical pharmacokinetic behavior (i.e., population pharmacokinetics), there is always a discrepancy between the predicted concentration and the actual concentration in the individual patient. It is important for the TCI user to understand that the predicted concentration reported by the TCI system is only an estimate. To use TCI systems intelligently, the user must have some sense of the accuracy of the predicted concentration.
Varvel et al.6
defined four parameters that are useful in the assessment of TCI performance; all of these parameters are based on the Percentage Performance Error (PE), which is defined as:MATH
where Cm is the measured (actual) concentration and Cp is the predicted concentration. The Median Absolute Performance Error (MDAPE) is the median PE of the TCI system and is a measure of how close the predicted concentration is to the measured concentration (i.e.
, accuracy). A MDAPE of 20% would mean that half of the predictions would be within 20% or closer to the targeted value and half would be outside that range. The Median Prediction Error (MDPE) is a measure of the overall bias of the predictions; it indicates whether the TCI system systematically overshoots or undershoots the target. Divergence and wobble, the other two performance parameters, are measures of how the accuracy changes over time (how much it diverges) and how variable the performance is over time (how much it wobbles). These two parameters are important when the TCI system is used for prolonged periods (i.e.
, many hours to days, such as in an intensive care unit setting). 6
The four TCI performance parameters described by Varvel et al.
are calculated for individual subjects and then summarized across an entire population.
When these performance measures are applied to a wide variety of TCI systems (i.e.
, different software and hardware), the typical prediction error (MDAPE) ranges from approximately 15–30% and the typical bias (MDPE) ranges from 3–20%, although the bias should be very nearly zero when optimal kinetic parameter sets are used. 7–9
Interestingly, presumably because of intrasubject variability, programming a TCI system with an individual's personal pharmacokinetic parameters in research settings (this, of course, requires a separate study to estimate the individual's parameters) does not improve TCI performance dramatically. 10,11 Figure 2
is an example of typical TCI performance for the opioid fentanyl, showing the best, median, and worst performance when the system was used in 21 subjects. As demonstrated in figure 2
, on average the performance of the system is quite good, although some subjects are, obviously, poorly characterized by the population pharmacokinetic model.
Also, with regard to pharmacologic variability and TCI performance, it should be emphasized that pharmacologic variability is a function of biology, not technology. A TCI system neither amplifies nor reduces any underlying pharmacokinetic variability, except to the extent that a TCI system may reduce interpatient variability by calculating the influence of covariate effects (e.g., the effect of age and weight) on the pharmacokinetics. TCI systems can also reduce the time-dependent variability in concentration that necessarily occurs with constant rate infusions because of drug accumulation.
Problems and Controversies with TCI Systems.
There are some important unsolved problems, limitations, and controversies surrounding TCI systems. The most obvious limitation is that TCI systems can only be as good as the pharmacokinetic model with which they are programmed. It is clear that some pharmacokinetic parameter sets for a given drug perform better than others when used to deliver a drug by computer. Which pharmacokinetic model parameter sets perform best and why is an area of intense investigation. 12
Other TCI controversies relate to the problem of plasma-effect site dysequilibrium. This is an important issue in that the effect site, or “biophase” concentrations, not the plasma concentrations, best correlate with drug effect. Although the plasma has been the target site for most early TCI applications, the effect site is the more logical target. 13,14
When targeting the plasma concentration, there is a significant delay in the achievement of a stable level of drug effect for many drugs; targeting the effect site results in faster attainment of therapeutic concentrations in the biophase, although this advantage may be associated with a slightly greater incidence of adverse events (e.g.
, hypotension). 13
Another unresolved problem associated with TCI is the search for an adequate method to define and describe appropriate IV anesthetic concentration targets (i.e., a “MAC” equivalent for IV drugs). Intravenous anesthetic pharmacodynamics have traditionally been characterized in terms of a CP50, the steady-state plasma concentration required to produce a 50% probability of some specified effect. However, it is somewhat difficult to apply this information to the selection of an appropriate TCI target, because the methods used to identify these CP50s have not been fully standardized as with MAC (some CP50s relate to loss of consciousness, others to movement and hemodynamics; some are estimated in the presence of other drugs, etc.). How IV anesthetic CP50s estimated from such diverse circumstances can be rationally applied to the selection of TCI targets for a given operation and anesthetic technique is not well understood. It is clear that the typical clinician has much more familiarity with MAC than with this much more diverse IV anesthetic CP50 data.
An important controversy surrounding TCI in the United States (and elsewhere, including Canada) relates to regulatory rather than scientific issues. The U.S. Food and Drug Administration has guidelines regarding combination products, but because TCI technology is a device inseparably connected to a drug, complexities arise in terms of whether the technology ought to be regulated as a drug or as a device. The lack of precedent for TCI system approval in the United States no doubt represents a significant obstacle to the commercial development of the technology. The uncertainty of the regulatory issues surrounding TCI in the United States likely prevents capable companies from being sufficiently motivated to pursue development of TCI technology for the U.S. market as they have in other countries. Although many North American–based clinician-scientists have played important roles in the development of TCI concepts and technology, 8,15
TCI technology is still restricted to the research domain in the United States. This is perplexing from a scientific perspective because TCI systems deliver approved drugs in approved doses via
approved routes for approved indications, perhaps with improved safety and efficacy, although almost certainly with no worse.
Current TCI State of the Art
TCI is actually a well-established technology that has been used in research and clinical care for many years. The first description of a TCI system dates to the early 1980s, when Schwilden et al.
developed a TCI system to infuse etomidate and alfentanil to provide anesthesia for gynecologic surgery. 16,17
Since then, a wide variety of TCI devices have been produced to infuse an array of drugs, including sedatives, analgesics, and muscle relaxants. 18–20
Perhaps because of its short-acting pharmacokinetic profile, propofol has become the most often-infused drug by TCI.
A proprietary propofol TCI system has now been in widespread clinical use in the majority of developed countries for over 6 yr. 21,22
Over 17,000 of these systems have been used for an estimated 13 million patients (personal written communication, May 6, 2003, John (Iain) B. Glen, Ph.D., Glen Pharma Ltd., Cheshire, United Kingdom). With the exception of a technical issue relating to a specific manufacturer's pump hardware (not the TCI software) that led to the under-delivery of propofol and intraoperative awareness in a small number of cases, 23
reports raising safety concerns about the technology have not appeared in the literature.
TCI systems have also been well received in clinical settings outside the operating room. For example, propofol TCI systems have now been extended beyond their use for general anesthesia to the conscious sedation/analgesia domain with promising results. 24
A TCI system using alfentanil has been applied to patient-controlled analgesia management of postoperative pain (when the user indicates inadequate pain relief by pressing the “button,” the alfentanil target is increased). 25
TCI systems have also been applied to the sedation of mechanically ventilated patients. 20
There is evidence that TCI systems can improve certain outcomes (e.g.
, intraoperative hemodynamics, the need for reversal agents, the speed of recovery), 26–29
although it has been difficult to demonstrate a truly compelling outcome improvement with the technology. Interestingly, most users tend to prefer TCI systems to manual infusions. 30
If and until large outcome trials demonstrate a clear improvement in outcome through using TCI, in the clinical setting the technology is probably best viewed as an incremental advance and not as truly revolutionary.
Although it is perhaps still unclear exactly what role computer-controlled drug delivery will play in clinical anesthesiology 10–20 yr in the future, its position in clinical pharmacology research is now already solidified. It is impossible to make meaningful pharmacodynamic observations without controlling the pharmacokinetic aspects of an experiment. TCI systems enable the investigator to establish a steady-state concentration of drug very near a target concentration so that pharmacodynamic measurements can be made without concern that drug levels are rapidly changing or are out of the intended range. Using TCI systems for pharmacokinetic control of a pharmacodynamic experiment has become a frequently applied and indispensable method in anesthesia clinical pharmacology research. 10,31,32
Another firmly entrenched research application of TCI systems is the use of simulation, requiring only the software of a TCI system, not the hardware. Through simulation of TCI drug delivery, it is possible to make comparisons about the clinical pharmacology of two drugs that are not possible in any other way. The context-sensitive half-time is just one example of TCI simulation. 33
Defined as the time required to achieve a 50% decrease in concentration after termination of a continuous infusion targeted to maintain a steady-state concentration, the context-sensitive half-time has been used to compare the clinical behavior of individual drugs within a selected drug class. Figure 3
illustrates the context-sensitive half-times of the fentanyl congeners. 34
The context-sensitive half-time has important implications in terms of rational drug selection and administration in anesthesiology. 35
TCI simulation software can be downloaded from a number of sites on the internet (e.g.
, accessed June 15, 2003.)
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