Weight loss and metabolic changes of morbidly obese patients after gastric partitioning operation.

UNLABELLED: Weight loss, alterations in basal metabolic rate, and utilization of body fat, carbohydrate, and protein substrates were studied in nine patients before operation and 3 and 12 months after gastric partitioning operation for morbid obesity. Respiratory oxygen consumption and carbon dioxide excretion measurements were taken three consecutive mornings by the open circuit-Scholander technique. Measurements of urine urea nitrogen were made from 24-hour urine collections. Basal metabolic rate and utilization of fat, carbohydrate, and protein were calculated in kilocalories per minute by indirect calorimetry. Initial body weight was 124.5 +/- 19.0 kg (mean +/- SD). The weight losses between measurements at months 0 and 3 and at months 3 and 12 were 20.8 +/- 4.6 kg and 2.7 +/- 8.4 kg, respectively. Total weight loss between months 0 and 12 was 23.5 +/- 8.3 kg (19.3% +/- 7.4%). At 3 months the fraction of basal metabolic rate contributed by carbohydrate (p less than 0.05) and protein (p less than 0.01) utilization decreased significantly, while that contributed by fat increased (p less than 0.05). Between months 0 and 12 there was no significant difference in protein or carbohydrate utilization, but fat utilization increased (p less than 0.10). CONCLUSIONS: Gastric partitioning operation resulted in an initial rapid body weight loss over 3 months with a sustained reduction over 1 year; there was a metabolic utilization shift to fat with carbohydrate and protein sparing; no metabolic parameter was predictive of weight loss; and temporally, the rapid weight loss was paralleled by a significant metabolic utilization shift, and the sustained loss was paralleled by a stabilization of this shift.

A prototype gas exchange monitor for exercise stress testing aboard NASA Space Station.

A monitor was developed to track weightlessness deconditioning aboard the National Aeronautics and Space Administration (NASA) Space Station by measuring the O2 uptake (VO2) and CO2 production (VCO2) and calculating maximum VO2 and anaerobic threshold during an exercise stress test. The system uses two flowmeters in series to achieve a completely automatic flow calibration, and it uses breath-by-breath compensation for sample line transport delay. The accuracy of the system was measured over the range of VO2 and VCO2 from 100 to 800 ml/min by means of simulation. Accuracy was 0.54% for VO2 and 2.9% for VCO2. The system was further evaluated using two laboratory methods, the first method being comparison with a breath-by-breath system. As volunteers performed a maximum effort on a cycle ergometer, the mean difference in readings between the two systems was 17 ml/min for VO2 and 8.0 ml/min for VCO2. The correlation coefficient squared was greater than 0.96 for both. The second laboratory test was to use the system for 2 mo in a Human Performance Laboratory. Readings of maximum VO2 (VO2max) and anaerobic threshold were repeatable and consistent with the individual's activity level. The accuracy and convenience of operation will make this a valuable instrument aboard the Space Station.

Calculation of metabolic expenditure and substrate utilization from gas exchange measurements.

At least nine different equations have been published for calculating metabolic expenditure by indirect calorimetry. This study examined the differences between equations when they are used for the nutritional assessment in an intensive care unit (ICU). Oxygen consumption and carbon dioxide production were measured in 36 ICU patients and used to calculate metabolic expenditure with the nine equations. The equations produced differences in metabolic expenditure which averaged from 0.8-96 kcal/day. The largest difference produced by any two of the nine equations was 189 kcal/day. Although differences in original stoichiometric data have resulted in numerous different equations for the calculation of metabolic expenditure, these differences are not clinically important. It makes little difference which equation is used for nutritional assessment in an ICU.

Fuzzy logic for model adaptation of a pharmacokinetic-based closed loop delivery system for pancuronium.

In this paper, we investigate the ability of fuzzy to adapt the parameters of a pharmacokinetic and pharmacodynamic model-based controller for the delivery of the muscle relaxant pancuronium. The system uses the model to control the rate of drug delivery and uses feedback from a sensor which measures muscle relaxation level to adapt the model using fuzzy logic. The control strategy administers mini-bolus doses of pancuronium and modulates the magnitude and time interval between the bolus doses to maintain a patient's muscle relaxation within an allowable range specified by the user. Before each new dose is given, the fuzzy logic adaptation scheme uses the error between the predicted patient response and the measured response to adapt the model. The system was tested using computer simulation by varying the parameters of the model by 50% from their nominal values. It was also evaluated in a clinical trial of five patients undergoing surgical procedures lasting 5 h or longer.

Theoretical analysis of non-invasive oscillometric maximum amplitude algorithm for estimating mean blood pressure.

A theoretical analysis is performed to evaluate the effect of arterial mechanical and blood pressure pulse properties on the accuracy of non-invasive oscillometric maximum amplitude algorithm (MAA) estimates of the mean blood pressure obtained using air-filled occlusive cuffs. Invasively recorded blood pressure pulses, selected for their varied shapes, are scaled to simulate a wide range of blood pulse pressures (diastolic blood pressure minus systolic blood pressure). Each scaled blood pressure pulse is transformed through an exponential model of an artery to create a series of blood volume pulses from which a simulated oscillometric waveform is created and the corresponding MAA estimate of the mean blood pressure and error (mean blood pressure minus MAA estimate) are determined. The MAA estimates are found to depend on the arterial blood pressure. The errors are found to depend on the arterial mechanical properties, blood pressure pulse shape and blood pulse pressure. These results suggest that there is no direct relationship between the mean blood pressure and MAA estimate, and that multiple variables may affect the accuracy of MAA estimates of the mean blood pressure obtained using air-filled occlusive cuffs.

Fundamentals of feedback control: PID, fuzzy logic, and neural networks.

Feedback controllers have been shown to bring blood pressure, muscle relaxation, inhalation drug concentration, and ventilation to the target level and keep it at the target as quickly and as accurately as can a well-trained clinician. Feedback control is an effective and convenient clinical tool for optimizing the day-to-day delivery of anesthetics, reducing induction time, delivering a minimum amount of drug, and avoiding costly delays from failing to keep the patient in a desired state.

Clinical analysis of the flexor hallucis brevis as an alternative site for monitoring neuromuscular block from mivacurium.

STUDY OBJECTIVES: To compare the flexor hallucis brevis, which is responsible for flexion of the great toe, to the adductor pollicis as a site for monitoring the onset and recovery from neuromuscular block after an intubating dose of mivacurium chloride. DESIGN: Prospective patient-controlled study. SETTING: University teaching hospital. PATIENTS: 10 ASA physical status I and II adults (age 18 to 55 years, 6 women, 4 men) scheduled for elective procedures requiring muscle relaxation for tracheal intubation. MEASUREMENTS AND MAIN RESULTS: Patients were monitored at the adductor pollicis and the flexor hallucis brevis during the onset and recovery of neuromuscular block, which was administered to facilitate tracheal intubation. All subjects were given mivacurium 0.2 mg/kg over 30 seconds. Their train-of-four (TOF) response was continually monitored at both sites until the patient recovered from the intubating dose to a TOF ratio of 0.75. The time to onset of neuromuscular block, recovery of the first TOF response, and recovery to a TOF ratio of 0.75 were compared between the two monitoring sites using the Wilcoxon signed rank test. Following administration of the intubating dose of mivacurium, the loss of all twitch response occurred 1.2 minutes sooner at the adductor pollicis than at the flexor hallucis brevis (p < 0.02). Reappearance of the first twitch occurred 0.49 minutes slower at the adductor pollicis, although this difference was not statistically significant. The time to recovery to a TOF ratio of 0.75 at the adductor pollicis was slower by 2.83 minutes (p = 0.046). CONCLUSIONS: Due to its lag behind the adductor pollicis, the flexor hallucis brevis is not a good indicator of when to intubate the trachea during the onset of neuromuscular block; however, its faster recovery may make it useful for monitoring deep neuromuscular block intraoperatively or during recovery when the adductor pollicis TOF response still shows complete blockade.

Computers in critical care.

This article reviews the current state-of-the-art and future applications of computers in critical care, with particular attention to ventilator and drug-delivery applications. Automated charting, alerts and alarms, and tools for decision support (such as expert systems and closed-loop control) are discussed also.

Closed-loop control of blood pressure, ventilation, and anesthesia delivery.

Closed-loop control systems have been in use for over 4,000 years, yet applications in medicine have developed only recently. When compared with manual control, closed-loop controllers for blood pressure, ventilation, and anesthesia delivery provide more rapid and more precise control of mean pressure, end-tidal CO2, and end-tidal anesthetic concentrations. Closed-loop control systems perform better in almost all situations. It must be remembered however, that the best anesthesiologist may perform better than the controller, particularly in his ability to anticipate clinical events which effect control. Although the convenience, precision of control, and immunity to distractions are reason enough to further pursue their development, their final application to clinical care will depend on the inclusion of appropriate safeguards and supervisory software algorithms to protect the systems from failure.

Fundamentals of feedback control applied to microcomputer instrumentation design.

Feedback control is widely used in applications which range from simple control of room temperature to very sophisticated control of space flight. This paper describes some fundamentals of feedback control as they apply specifically to microcomputer based medical devices. A classical controller is described in its analog and digital implementations. Reference is made to methods for adjusting or tuning the controller for specific applications. Successful applications of adaptive or self-tuning control are discussed. Examples of feedback control include systems to control arterial blood pressure by the infusion of sodium nitroprusside, systems to control arterial carbon dioxide concentration by mechanical ventilation and systems to control depth of anesthesia by controlled anesthesia delivery.

How the rise time of carbon dioxide analysers influences the accuracy of carbon dioxide measurements.

Carbon dioxide measurements are not accurate, especially in children, if the response time of the carbon dioxide analyser is too slow and its output fails to reach the actual carbon dioxide concentration at the end of the breath. The distortion of the carbon dioxide waveform is a function of the "rise time" of the analyser. We have simulated an expired carbon dioxide curve and calculated the rise time required to measure accurately end-tidal carbon dioxide and VCO2 in adults and children. A rise time of 80 ms (10-70%) is sufficient to measure end-tidal carbon dioxide concentration with 5% accuracy in patients with rates of ventilation less than 100 b.p.m. and I:E ratios less than 2:1. We have measured the rise time of 11 commercially available carbon dioxide analysers and found that only six of the 11 responded quickly enough to be accurate for rates up to 100 b.p.m. All 11 responded rapidly enough to measure end-tidal carbon dioxide concentration with 5% accuracy when ventilatory rates were less than 30 b.p.m. To measure VCO2 with 5% accuracy, an analyser should have a rise time of 20 ms. Only one analyser met this specification. An analyser's rise time can be estimated clinically to within 10 (SD 8) ms by a simple breath hold and forced exhalation, thus providing an estimate of the accuracy of carbon dioxide measurements in adults or children.

Device to limit inflation of a pulmonary artery catheter balloon.

OBJECTIVE: The most serious complication seen with pulmonary artery catheters is rupture of the pulmonary artery. The effectiveness of an external safety balloon added to the pulmonary artery balloon inflation port was tested. DESIGN: The external balloon is designed to inflate and absorb excess volume from the inflation syringe after the internal balloon contacts the vessel wall. When the catheter tip is in a small pulmonary artery, expansion of the external balloon indicates that the catheter tip is in a noncompliant or small vessel. SETTING: The external balloon was tested in a bench simulation. INTERVENTIONS: None. MEASUREMENTS AND MAIN RESULTS: The pulmonary artery balloon was slowly inflated inside 2.6-, 3.0-, 4.7-, 8.6-, and 11.6-mm internal diameter polyvinyl chloride tubes, with and without the external safety device in place. Without the external balloon, the average balloon pressure was 1647 +/- 145 (SD) mm Hg in the 2.6-mm vessel. With the external balloon in use, the maximum pulmonary artery balloon pressure was 473 +/- 7.2 mm Hg in the 2.6-mm vessel. CONCLUSIONS: The external balloon can limit balloon pressures within the pulmonary artery and identify when excessive volumes are being forced into the pulmonary artery balloon.

Closed-loop control for anesthesia breathing systems.

Numerous medical applications of closed-loop control have been developed over the past 40 years. For the patient breathing system, appropriate sensors are available. Feedback controllers have been developed and tested. Gas and vapor delivery devices seem ready for use. With the sensors, controllers, and delivery devices developed and tested, it seems likely that closed-loop control will be an integral part of future anesthesia workstations. The convenience and improved stability and response time will be important advantages in future anesthesia delivery systems.

A simulation of neuromuscular function and heart rate during induction, maintenance, and reversal of neuromuscular blockade.

We developed a two-compartment model to simulate neuromuscular function and heart rate following the administration of four nondepolarizing neuromuscular blocking agents (atracurium, vecuronium, pancuronium, and d-tubocurarine), three neuromuscular block reversal agents (edrophonium, neostigmine, and pyridostigmine), and two anticholinergic agents (atropine and glycopyrrolate). Twitch depression, train-of-four ratio, and heart rate were modeled during fentanyl, halothane, enflurane, or isoflurane anesthesia, optionally supplemented with nitrous oxide. Simulation results, compared with published values for each drug, fell within the clinical accuracy range (onset time 6.1 +/- 3.9% [mean +/- SEM]; duration, 1.7 +/- 3.5%, 50% effective dose, 0.5 +/- 5.7%; and 95% effective dose, 2.1 +/- 1.1%). The simulation graphically demonstrates the pharmacokinetics, pharmacodynamics, and interactions between neuromuscular blocking agents, reversal agents, and anticholinergic agents. During a simulation, the need for frequent monitoring and repeated delivery of a neuromuscular blocking agent to keep neuromuscular blockade stable becomes apparent, especially with the intermediate-acting neuromuscular blocking agents. When inhalational agents are given concomitantly, the task becomes even more difficult, since potentiation changes with anesthetic uptake. Recurarization, tachycardia, or bradycardia may be seen with the simulation if an improper drug regimen is followed. Concurrent simulation of two identical patients allows comparison of different modes of administration, choice of anesthetic agents, and drug doses.