ELIMINATION OF VAPOUR ANAESTHETICS FROM PATIENTS AFTER SURGICAL PROCEDURES

Abstract: A method of treatment of an animal to recover from vapour anaesthetics administration is provided, the method comprising delivering to a patient gases which do not contain CO2 at a specified rate, and gases containing CO2 to maintain the same PCO2 in the animal independent of the rate of ventilation, at the rate of ventilation of the animal which exceeds the rate of administration of the gases which do not contain CO2.

Description: TITLE OF INVENTION Elimination of vapour anaesthetics from patients after surgical procedures FIELD OF INVENTION The purpose of this invention is to provide a simple breathing circuit that can, for example, be added to a standard circle anaesthetic circuit known to persons skilled in the art to hasten recovery of patients administered vapour anaesthetics prior to an operation. This invention also relates to the use of the breathing circuit in hastening the recovery of patients who have been administered vapour anaesthetics prior to a surgical operation. This invention also relates to methods of treatment of patients to hasten their recovery from administration of the vapour anaesthetics to them prior to surgical procedures. BACKGROUND OF THE INVENTION Physiology Venous blood returns to the heart from the muscles and organs depleted of oxygen (O 2 ) and full of carbon dioxide (CO?). Blood from various parts of the body is mixed in the heart (mixed venous blood) and pumped to the lungs. In the lungs the blood vessels break up into a net of small vessels surrounding tiny lung sacs (alveoli). The net of vessels surrounding the alveoli provides a large surface area for the exchange of gases by diffusion along their concentration gradients. A concentration gradient exists between the partial pressure of C0 2 (PC0 2 ) in the mixed venous blood (PvCQ 2 and the alveolar PC0 2 . The C0 2 diffuses into the alveoli from the mixed venous blood from the beginning of inspiration until an equilibrium is reached between the PvC0 2 and the alveolar PC0 2 at some time during the breath. When the subject exhales, the end of his exhalation is considered to have come from the alveoli and reflect the equilibrium concentration between the capillaries and the alveoli; the PC0 2 in this gas is (PETCQ 2 ). When the blood passes the alveoli and is pumped by the heart to the arteries it is known as the arterial PCOi (PaCO ? ). The arterial blood has a PC0 2 equal to the PC0 2 at equilibrium between the capillaries and alveoli. With each breath some C0 2 is eliminated and fresh air containing little C0 2 (assumed to be O) is inhaled and dilutes the residual alveolar PC0 2 , establishing a new gradient for C0 2 to diffuse out of the mixed venous blood into the alveoli. The rate of breathing, or ventilation (V), usually expressed in L/min, is exactly that required to eliminate the C0 2 brought to the lungs and maintain an equilibrium PC0 2 (and PaC0 2 ) of approximately 40 mmHg (in normal humans). When one produces more C0 2 ( e.g. as a result of fever or exercise), more C0 2 is produced and carried to the lungs. One then has to breathe harder (hyperventilate) to wash out the extra C0 2 from the alveoli, and thus maintain the same equilibrium PaC0 2 . But if the C0 2 production stays normal, and one hyperventilates, then the PaC0 2 falls. It is important to note that not all V contributes to blowing off C0 2 . Some V goes to the air passages (trachea and bronchi) and alveoli with little blood perfusing them, and thus doesn't contribute to blowing off C0 2 . That portion of V that goes to well perfused alveoli and participates in gas exchange is called the alveolar ventilation (VA). There are a number of circumstances in therapeutic medicine and research where we want the subject to breathe harder but not change his PaC0 2 (see Table 1). Table 1 Type of Investigation Reference Method of Source of C0 2 adjustment Respiratory muscle fatigue 5 M R 12 M E 7 M R Respiratory muscle training 2 M R 3 M R Increased V during 6 M R anaesthesia Carotid chemoreceptor 8 M E function 1 M E Effect of hypoxia on 10 M E sympathetic response 4 M E Control of respiration 9 A E Tracheobronchial tone 11 M E Table 1: Title: Summary of previous studies attempting to maintain constant PETCO2 during hyperpnea Legend: Method of adjustment of inspired PCO2 : M = manual; A = automated. Source of CO2: R = rebreathing; E = external. 1. Angell-James, J.E., Clarke, J.A., de Burgh Daly, M. and Taton, A., Carotid chemoreceptor function and structure in the atherosclerotic rabbit: respiratory and cardiovascular responses to hyperoxia and hypercapnia. Cardiovascular Research 23(6): 541-53, 1989. 2. Belman, M.J. and C. Mittman. Ventilatory muscle training improves exercise capacity in chronic obstructive pulmonary disease patients. Am. Rev. Respir. Dis. 121:273-280, 1980. 3. Bradley, M.E. and Leith, D.E. Ventilatory muscle training and the oxygen cost of sustained hyperpnea. /. Appl. Physiol. 45(6):885- 892,1978. 4. Busija, D.W., Orr, J.A., Rankin, J.G.H., Liang, H.K. and Wagerle, L.C., Cerebral blood flow during normocapnic hyperoxia in the unanaesthetized pony. /. Apple. Physiol. 48(1):10-15, 1980. 5. Jonsson, L.O. Predictable PaCθ2 with two different flow settings using the Mapleson D. system. Ada Anaesthesiol Scand. 34:237-240, 1990. 6. McKerrow, C.B., and Otis, A.B. Oxygen cost of hyperventilation. /. Apple. Physiol. 9:375-79, 1956. 7. Robbins, P.A., Swanson, G.D. and Howson, M.G. A prediction- correction scheme for forcing alveolar gases along certain time courses. /. Apple. Physiol. 52(5):1353-1357, 1982. 8. Smith, D.M., Mercer, R.R. and Eldridge, F.L., Servo control of end- tidal CO2 in paralyzed animals. /. Apple. Physiol. 45(1):133-136, 1978. 9. Somers, V.K., Mark, A.L., Zavala, D.C. and Abboud, F.M. Influence of ventilation of hypocapnia on sympathetic nerve responses to hypoxia in normal humans. /. Appl. Physiol. 67(5):2095-2100, 1989. 10. Sorkness, R. and Vidruk, E. Reflex effects of isocapnic changes in ventilation of tracheal tone in awake dogs. Respir. Physiol. 69:161- 172, 1987. 11. Tenney, S.M. and Reese, R.E. The ability to sustain great breathing efforts. Respir. Physiol. 5:187-201, 1968. 12. Wahba, R.W.M. and Tessler, M.J. Misleading end-tidal CO2 tensions. Can. J. Anaesth. 43(8):862-6, 1996. This requires compensating for excess ventilation by inhaling C0 2 either from exhaled gas or some external source. The amount of C0 2 required to be inhaled needs to be adjusted manually or by an automated servo-controlled mechanism, depending on how fine the control of PaC0 2 is required. The input signal is the PETCO 2 • Stability of PaC0 2 depends on the variability of C0 2 production and ventilation on the one hand, and the ability of a system to compensate for this variability on the other. The termination of the anaesthetic effects of intravenously administered drugs depends on metabolism and redistribution. The recovery time from anaesthesia is therefore determined by the drug's pharmacology and cannot be accelerated. This is not so for inhaled anaesthetic vapours. The uptake and elimination of anaesthetic vapours is predominantly through the lungs. The partial pressure of an anaesthetic vapour in the blood going to the brain is dependent upon the equilibration of vapour between the blood and the lungs. The concentration of vapour in the lungs in turn is dependent on the concentration of vapour in the inhaled gas, the rate of breathing, and the rate of transfer of gas between the lung and the blood. The newer anaesthetic agents desflurane and sevoflurane have very low blood solubility. Therefore the amount of drug transferred between the lungs and the blood is small and can, for discussion purposes, be ignored. Thus, for a patient waking up from a vapour anaesthetic, the greater the rate of breathing, the more vapour is eliminated from the lungs. However, in anaesthetized patients breathing spontaneously, ventilation is often depressed as a result of combined effects of residual intravenously administered anaesthetic drugs, pain relieving drugs (i.e. narcotics), the effects of surgery, as well as the respiratory depressant effect of the residual anaesthetic vapour itself Practically, there has been limited scope for intervention to hasten the process of eliminating vapour from the lung and thus hastening the rate of emergence from the effects of vapour anaesthesia. Proposals in Prior Art 1. Artificial ventilation Manually or mechanically hyperventilating patients at the end of surgery is generally ineffective in shortening the time of recovery from anaesthesia. a) High ventilation using the circle anaesthetic circuit results in rebreathing of exhaled gases. These gases contain anaesthetic vapour as well as C0 2 . The C0 2 is eliminated by the C0 2 absorber in the circuit, but the exhaled anaesthetic vapour is returned to the patient. b) The attempts at hyperventilation will result in a decrease in arterial PC0 2 . The low arterial PC0 2 removes the stimulus to breathe, which in turn delays elimination of vapour (and may also prevent adequate oxygenation of the blood). This is seldom practised. 2. Flushing the circuit: High fresh gas flows in the circuit are inefficient in washing out the vapour from the circuits. The circle anaesthetic circuits have volumes of approximately 8 L (not counting the patient's lung volume of approximately 2.5 L). At the maximum fresh gas flows on the oxygen flow meter of 10 L/min, it would take about 4 minutes to wash out the anaesthetic vapour from the circuit alone! 3. Stimulate breathing In the past, some anaesthetists tried to stimulate the patient's breathing by adding C0 2 to the breathing circuit. The rationale was to increase the C0 2 concentration in the circuit, stimulate the patient to breathe harder until he managed to ventilate off the C0 2 and some of the vapour as well. This has largely been abandoned and has been labeled a wasteful and dangerous practice. a) It is wasteful for the reasons enumerated in la and lb (vide supra). As well, the practice is wasteful in that extra C0 2 absorbing crystals are consumed. b) The technique may put a patient at risk if the patient cannot respond to the extra C0 2 by increasing their ventilation. They will absorb it and develop a high blood C0 2 concentration which can be detrimental. The high C0 2 in the patient also causes them a good deal of distress on waking up as it makes them feel like they are not getting enough air to breathe. 4. Increase ventilation, keeping PC0 2 constant To increase the ventilation without lowering PC0 2 requires adding C0 2 to the circuit. This can be supplied from an external source or from the subject's exhaled gas. All the presently described systems depend on a servo-controlled system, or feedback loop to regulate the amount of C0 2 supplied to the patient. These devices are complex, cumbersome and expensive. No such device has been reported used for hastening the elimination of anaesthetic vapour during recovery from anaesthesia. With respect to 4 above, there are considerable limitations of servo- controlled methods, both manual or automatic. These may be discussed as follows: 1. Input signal Whereas the parameter that we want to keep constant is the arterial PC0 2/ feedback systems use the C0 2 concentration in the expired gas, the so called end tidal PC0 2 (PETC0 2 ) as the input signal and endpoint. The PETC0 2 can be very different from the arterial PC0 2 in many circumstances. Furthermore, changes in PETC0 2 may not correlate with those in arterial PC0 2 . This will result in PETC0 2 being an inappropriate input for the control of arterial PC0 2 - For example, a smaller than usual breath decreases PETC0 2 (tending to increase arterial PC0 2 ), causing a servo-controller to respond with an inappropriate increase in inspired C0 2 . 2. Gain If, in an attempt to obtain fine control, the gain in a servo-control system is set too high, the response becomes unstable and may result in oscillation of the control variable. Conversely, if the gain is set too low, compensation lags. Over-damping of the signal results in a the response never reaching the target. To address these problems, servo-controllers require complex algorithms and expensive equipment. 3. Inherent limitation Servo-control systems work on the principle of detecting, and subsequently attempting to correct for, changes in PETC0 2 . Even under ideal conditions, no such system can predict the size of an impending VT in a spontaneously breathing subject and thus deliver the appropriate C0 2 load. As is apparent, people have tried to hasten the recovery of patients who have been anaesthetized and have made substantial efforts in this regard. However, they have been, for the most part, as seen above, unsuccessful. The reason for the attempts is that the benefits of faster return to consciousness, the less the need for recovery care and the less risk of nausea and post-operative respiratory complications. Thus the health care system will save substantial dollars. In this regard, the cost to the health care system of operating room and recovery area time is approximately $5.00 (Canadian Dollars) and $2.00 (Canadian Dollars) per minute respectively. The total number of anaesthetics given in North America is approximately 35,000,000/year (3.5 million and about 30 million in the United States), a conservative estimate with as high as about 50,000,000 /year. The North American estimate does not include Mexico or countries in Central America. A modest average decrease in recovery time in the operating time and in the recovery room of 5 minutes each can potentially result in billions of dollars savings per year worldwide. In North America alone, the expectation of saving 5 minutes in each of the operating room and recovery area can amount to $1,000,000,000 in savings. It is therefore an object of this invention to provide an improved breathing circuit or circuit components that can be added to a standard circle anaesthetic circuit to be used to hasten recovery of patients who have been administered vapour anaesthetics. It is a further object of the invention to provide methods of treatment using the said circuit and the use of the said circuit during the administration of vapour anaesthetics to hasten recovery of the said patients. Further and other objects of the invention will be realized by those skilled in the art reading the following summary of the invention and detailed description of embodiments thereof. SUMMARY OF THE INVENTION According to one aspect of the invention, there is provided a new breathing circuit and components thereof that can, for example, be added to a standard circle anaesthetic circuit for hastening the recovery of patients administered vapour anaesthetics. In accordance with the invention, the said circuit and components thereof, when combined with the general anaesthetic circle circuit cause the administration of carbon dioxide gas to the patient to maintain the same PC0 2 in the patient independent of the rate of ventilation (so long as the said rate of ventilation is greater than a control rate of ventilation) but permit the rate of anaesthetic vapour elimination from the lungs of the patient to vary directly as the total ventilation by the patient, whether the patient is breathing normally or is hyperventilating. Thus, the vapour anaesthetic is eliminated from the lungs. However, the carbon dioxide is not eliminated from the lungs at a rate greater than the resting rate of the patient or a predetermined control rate. (The predetermined rate of elimination of CO 2 may be set based on the rate of administration of the fresh gas into the circuit as discussed below.) Thus, according to another aspect of the invention, the simple breathing circuit comprises components which together form the simple circuit and comprise (a) an exit port from which the gases exit from the circuit to the patient, (b) a non-rebreathing valve which constitutes a oneway valve permitting gases to be delivered to the exit port to be delivered to the patient but which non-breathing valve when the patient breathes into the exit port does not permit the gases to pass the non-rebreathing valve into the portion of the circuit from which the gases are delivered but passes them to ambient or elsewhere, (c) a source of gas (which may be oxygen or air or other gases but does not contain CO 2 (air contains physiologically insignificant amounts of CO 2 ) in communication with the non-breathing valve to be delivered through the valve to the patient, (d) a fresh gas reservoir in communication with the source of fresh gas flow for receiving excess gas not breathed by the patient from the source of gas and for storing same and when the patient breathes and withdraws amounts of gas from the source of gas flow also enables the patient to receive gas from the fresh gas reservoir in which the gases have been stored, (e) a reserve gas supply containing CO 2 and other gases (usually oxygen) wherein the partial pressure of the CO 2 is approximately equal to the partial pressure of the CO 2 in the patient's mixed venous blood, for being delivered to the non-rebreathing valve as required by the patient to make up that amount of gas required by the patient when breathing that is not fulfilled from the gases delivered from the source of gas flow and fresh gas reservoir, the said source of gas and fresh gas reservoir and reserve gas supply being disposed on the side of the valve remote from the exit port. Preferably a pressure relief valve is in communication with the fresh gas reservoir, in the event that the fresh gas reservoir overfills with gas so that the fresh gas reservoir does not break, rupture or become damaged in any way. The reserve gas supply preferably includes a demand valve regulator so that where the additional gas is required, the demand valve regulator opens the communication of the reserve gas supply to the non- rebreathing valve for delivery of the gas to the non-breathing valve and where not required the demand valve regulator is closed and only fresh gas flows from the source of fresh gas and from the fresh gas reservoir to the non-rebreathing valve. The source of fresh gas is set to supply fresh gas (non-Cθ2-containing gas) at a rate equal to the desired alveolar ventilation for the elimination of CO2. The basic concept underlying my approach is that when breathing increases, the rate of flow of fresh gas (inspired PC0 2 = 0) from the fresh gas flow contributing to elimination of C0 2 is kept constant. The remainder of the gas inhaled by the subject (from the reserve gas supply) has a PC0 2 equal to that of mixed venous blood, does not contribute to a C0 2 concentration gradient between mixed venous blood and alveolar gas, and thus does not contribute to elimination of C0 2 . If there is access to mixed venous blood (such as if a catheter is present in the pulmonary artery, the mixed venous PC0 2 can be measured directly. If there is no possibility of measuring, then an estimation can be made from PETC0 2 . PETC 0 2 is determined by measuring the PC0 2 of expired using a capnograph usually present or easily available in an operating facility by persons skilled in the art. In effect, the device passively, precisely and continuously matches the amount of C0 2 breathed in by the patient to the amount of total breathing, thereby preventing any perturbation of the arterial PC02. This is opposed to servo-controllers which are always attempting to compensate for changes. Persons skilled in the art, however, may automate the circuit by using a servo-controller or computer to monitor and deliver the amounts from the reserve gas supply. According to another aspect of the invention, the new simple breathing circuit is used to treat a patient to enable the patient to recover more quickly from, and to hasten the recovery of the patient after, vapour anaesthetic administration. According to another aspect of the invention, the use of the said circuit is made in the manufacture of a device to hasten the recovery of patients from administration of vapour anaesthetics. According to another aspect of the invention, the use of the said circuit is made to hasten the recovery of patients from vapour anaesthetics administration. According to another aspect of the invention, a method of treatment of an animal (for example, a person) is provided (such as to enable such animal to recover from vapour anaesthetics administration), the method comprising delivering to a patient gases which do not contain CO2 at a specified rate, and gases containing CO2 to maintain the same PCO2 in the animal independent of the rate of ventilation, at the rate of ventilation of the animal which exceeds the rate of administration of the gases which do not contain CO2. Therefore, when the rate of ventilation of the animal exceeds the rate of delivery to the animal of non-Cθ2-containing gases inhaled by the animal, the Cθ2-containing gases inhaled by the animal maintain the PCO2 in the animal constant. Thus, with respect to the use of the invention to eliminate anaesthetic vapour from the lungs, the total ventilation of combined gases which includes the Cθ2-containing, and non-Cθ2 containing, gases act to eliminate vapour from the lungs. This circuit and methods of treatment can also be used for any circumstance where one wants to dissociate the minute ventilation from elimination of carbon dioxide such as respiratory muscle training, investigation of the role of pulmonary stretch receptors, tracheobronchial tone, expand the lung to prevent atelectasis, and control of respiration and other uses as would be understood by those skilled in the art. The circuit and methods of treatment may also be used by deep sea divers and astronauts to eliminate nitrogen from the body. It can also be used to treat carbon monoxide poisoning under normal baric or hyper baric conditions. The fresh gas will contain 100% oxygen, and the reserve gas will contain approximately 6% CO2 and approximately 94% oxygen. Neither the fresh gas nor the reserve gas supply will, in this case, contain nitrogen. BRIEF DESCRIPTION OF THE DRAWINGS Figure 1 illustrates schematically the nature of the simple breathing circuit and components which enable the patient to recover more quickly from vapour anaesthetics administration. The said device shown enables the PC0 2 to remain constant despite increase in minute ventilation which thereby permits faster elimination of the vapour anaesthetic. Figure 2 illustrates schematically portions of a standard circle anaesthetic circuit generally known to persons skilled in the art. Figure 3 illustrates schematically the simple breathing circuit in one embodiment added to the portions of the circle anaesthetic circuit shown schematically in Figure 2, illustrating modifications of the circuit shown schematically in Figure 1 for use with the generally known circuit shown in Figure 2. (It would be clear to persons skilled in the art that depending upon the circuit used as the circle anaesthetic circuit, different modifications on the basic circuit shown in Figure 1 will be made.) Figure 4A illustrates the structure shown in Figure 3, now combined with the general structure shown in Figure 2. (Figure 3 shows the modifications made specifically to the structure of Figure 1 to combine it with the structure in Figure 2 which is now shown in Figure 4 A.) Figures 4B and 4C illustrate schematically close up portions of one portion of the structure shown in Figure 4A in different positions. Figure 5 graphs the VT (Tidal Volume) and PETCO2. Figure 6 graphs traces of airway PCO2 and VT. Figures 7A, 7B and 8A and 8B graphically depict changes in PaCθ2 and PETCO2. DETAILED DESCRIPTION OF EMBODIMENTS The circuit (Figure 1) consists of a non-rebreathing valve (A) connected distally to two ports (C and D). The first port is connected in parallel to a source of fresh gas (E) (which does not contain CO2) and a fresh gas reservoir (F). A one-way pressure relief valve (G) prevents overfilling of the reservoir (F) by venting excess fresh gas. The second port (D) is connected via a one-way valve (H), to a source of gas (containing CO2) whose PC0 2 is equal approximately to that of the mixed venous PC0 2 . We call this the "reserve gas" (I). Non-rebreathing valve A is connected to exit port J (from which the patient breathes). Functional analysis of circuit maintaining constant PCO? with hyperventilation When the minute ventilation "V" is less than or equal to the fresh gas flow "FGF" from (E), the subject inhales only fresh gas (non-C0 2 - containing gas). When V exceeds FGF, the reservoir (F) containing fresh non-C0 2 -containing gas empties first and the balance of inhaled gas is drawn from the reserve gas (I) which contains C0 2 . The reserve gas is considered not to participate in C0 2 exchange ensuring that the actual ventilation provided is limited by FGF. If the rate of FGF is 5L/minute and the patient breathes at 5L/minute or less, then the patient will inhale only non-C0 2 -containing gas that comes from fresh gas flow sources (E and F). If minute ventilation exceeds FGF, the difference between minute ventilation and fresh gas flow is made up from gas from reserve gas (I) which contains C0 2 at a concentration that does not provide a gradient for elimination of C0 2 in the patient. Application of circuit to anaesthesia circle circuit The schematic of the standard anaesthetic circle circuit, spontaneous ventilation (Figure 2) When the patient exhales, the inspiratory valve (1) closes, the expiratory valve (2) opens and gas flows through the corrugated tubing making up the expiratory limb of the circuit (3) into the rebreathing bag (4). When the rebreathing bag is full, the airway pressure-limiting (APL) valve (5) opens and the balance of expired gas exits through the APL valve into a gas scavenger (not shown). When the patient inhales, the negative pressure in the circuit closes the expiratory valve (2), opens the inspiratory valve (1), and directs gas to flow through the corrugated tube making up the inspiratory limb of the circuit (6). Inspiration draws all of the gas from the fresh gas hose (7) and makes up the balance of the volume of the breath by drawing gas from the rebreathing bag (4). The gas from the rebreathing bag contains expired gas with C0 2 in it. This C0 2 is extracted as the gas passes through the C0 2 absorber (8) and thus is delivered to the patient (P) without C02, (but still containing exhaled anaesthetic vapour, if any). Modification of the circuit (Figure 3) to allow hyp r ventilation of patients under anaesthesia The modified circuit consists of 1. a circuit which acts functionally like a standard self inflating bag (such as made by Laerdal ) consisting of a) a non rebreathing valve, such as valve #560200 made by Laerdal, that functions during spontaneous breathing as well as manually assisted breathing (9); b) an expired gas manifold, such as the Expiratory Deviator #850500, to collect expired gas (10) and direct it to a gas scavenger system (not shown) or to the expiratory limb of the anaesthetic circuit (figure 4); c) a self inflating bag (11) whose entrance is guarded by a one way valve directing gas into the self inflating bag (12). 2. a source of fresh gas, (i.e. not containing vapour) e.g. oxygen or oxygen plus nitrous oxide (13) with a flow meter (22). 3. a manifold (14) with 4 ports: a) a port (15) for input of fresh gas (13); b) a port (16) for a fresh gas reservoir bag (17); c) a port to which is attached a one way inflow valve that opens when the pressure inside the manifold is 5cm H 2 0 less than atmospheric pressure, such as Livingston Health Care Services catalog part #9005, (18) (assuring that all of the fresh gas is utilized before opening); d) a bag of gas (19) whose PC0 2 is equal approximately to that of the mixed venous PC0 2 connected to inflow valve (18)(Alternatively, the valve and gas reservoir bag can be replaced by a demand regulator, such as Lifetronix MX91120012, similar to that used in SCUBA diving, and a cylinder of compressed gas); e) a port to which is attached a one way outflow valve (20), such as Livingston Health Care Services catalog part #9005, that allows release of gas from the manifold to atmosphere when the pressure in the manifold is greater than 5cm H2O. Method of operation in an anaesthetic circuit (Figure 4A) The distal end of the nonrebreathing valve (Laerdal type) (9), is attached to the patient. The proximal port of the nonrebreathing valve is attached to a 3 way respiratory valve (21) which can direct inspiratory gas either from the circle anaesthetic circuit (Figure 4B) or from the new circuit (Figure 4C). The expiratory manifold (10) of the self inflating bag's non rebreathing valve is attached to the expiratory limb of the anaesthetic circuit (3). Regardless of the source of inspired gas, exhalation is directed into the expiratory limb of the anaesthetic circuit. To maximize the elimination of anaesthetic vapour from the patient's lungs, the 3-way respiratory stopcock is turned such that patient inspiration is from the new circuit (Figure 4C). Thus inspired gas from the very first breath after turning the 3-way valve onward contains no vapour, providing the maximum gradient for anaesthetic vapour elimination. An increased breathing rate will further enhance the elimination of vapour from the lung. If breathing spontaneously, the patient can be stimulated to increase his minute ventilation by lowering the FGF (22) thereby allowing the PC0 2 to rise. Using this approach the PC0 2 will rise and plateau independent of the rate of breathing, resulting in a constant breathing stimulus. All of the ventilation is effective in eliminating vapour. If the patient is undergoing controlled ventilation, he can also be hyperventilated with the self-inflating bag (11). In either case, the patient's PC0 2 will be determined by the FGF (22). As long as the FGF remains constant, the PC0 2 will remain constant independent of the minute ventilation. To illustrate the effectiveness of the circuit we performed a number of tests with respect to humans and dogs. The humans were breathing spontaneously and the dogs were mechanically ventilated. Human subjects After obtaining institutional ethics board approval and informed consent, four healthy subjects aged 19 - 25 y breathed through the circuit by means of a mouth piece while wearing nose clips. During normal breathing, the FGF was set equal to V by adjusting the FGF such that the bag containing fresh gas just emptied at the end of each inhalation. Subjects were then instructed to breathe maximally ("breathe as hard as you can") for 3 min. Flows were recorded by means of a Pitot tube (Voltek Enterprises, Willowdale Canada) and the signal integrated to obtain volume. C0 2 was sampled continuously at the mouthpiece (Medical Gas Analyzer LB-2, Sensormedics Corp., Anaheim California). Analog signals _1 -were digitized at 60 samples-s and recorded using data acquisition software (WINDAQ/200, DATAQ instruments, Inc. Akron Ohio). Studies in dogs Following institutional ethics board approval, 6 mongrel dogs of either sex weighing 20-25kg were anaesthetized with methohexital (5-7 -1 -1 -1 mg-kg for induction followed by 150-300 mg-kg -min ) and intubated. Adequacy of anaesthetic depth was deduced from the eye lash reflex, lack of spontaneous movements, and stable heart rate and blood pressure. A catheter was placed in the femoral artery for monitoring blood pressure and periodic sampling of blood for gas analysis., The dogs were ventilated with a conventional mechanical piston ventilator (Harvard Apparatus model 618, South Natick, MA). For each dog, an inflation volume (VT) of 400 ml and a frequency (f) of 10 min (duty cycle, 0.5) were used. All dogs were ventilated to just below their apneic thresholds (by increasing VT about 50 mL) so that they made no respiratory efforts. Tidal C0 2 was sampled continuously (Ametek, Thermox Instruments Division, Pittsburgh, PA) at the proximal end of the endotracheal tube. Flow was measured with a pneumotachograph (Vertek series 47303A, Hewlett- Packard) and the signal integrated to obtain volume. Analog signals were - digitized at 17 samples-s and recorded using the same data acquisition software as that used in studies on human subjects. Because of differences in initial PaC0 2 s among dogs (reflecting individual sensitivities to C0 2 , differences in anaesthetic levels, or differences in Vτ/body weight ratio), the C0 2 concentration in the reserve gas was arbitrarily adjusted for each dog to 1.5 ± 0.5% above its FetC0 2 to approximate the mixed venous PC0 2 (PvC0 2 ) (see Table II). To allow greater flexibility in setting the concentration of C0 2 in the reserve gas, the circuit was modified by replacing the demand valve with a one-way PEEP (positive end expiratory pressure) valve and the cylinder with a bag containing premixed gas. This circuit is functionally identical to that used in studies on humans. The circuit was connected to the intake port of the ventilator. Under control conditions, FGF was adjusted so that the fresh gas reservoir just emptied during each ventilator cycle; this end point was confirmed by a slight rise in FIC0 2 above zero. After a steady-state had been reached (difference < 1.5 mm Hg in two successive PaC0 2 's taken 5 minutes apart), VT was increased at 5 minute intervals from 400 to 600 to 900 to 1200 mL. In a second trial at a fixed VT (approximately 400 mL) and fixed FGF, f was increased at 5 minute intervals from 10 to 14 to 18 to 22 min . A blood sample for the determination of blood gases was drawn from the femoral artery at the beginning and end of each 5 min interval. All data are expressed as means ± standard deviation. We tested for significant differences using one- or two-way ANOVA with post hoc analysis where appropriate. A p value less than 0.05 was considered significant. Results: Human subjects Figure 5 presents the VT and PETC0 2 of subject 1 during 3 min of maximal ventilatory effort. Results for all subjects are summarized in Table III; data represent average values for 10 breaths at 0 (the onset of hyperventilation), 1.5 and 3 min. PETC0 2 did not change significantly from control values throughout the course of hyperventilation (p = 0.08, ANOVA). There was considerable variability in V and breathing patterns between subjects but individual subjects tended to sustain a particular breathing pattern throughout the run. Dogs Figure 6 presents traces of airway PC0 2 and VT for dog #5 during changes in / or VT. Figures 7 and 8 show the changes in PaC0 2 and the PETC0 2 in all dogs during changes in / or VT. Increases in / did not significantly affect mean PaC0 2 or PETC0 2 (p=0.28 and p=0.11, respectively; ANOVA). Increases in VT decreased mean PaC0 2 from control only at VT of 1200 mL (p=0.01); in contrast, changes in VT did not affect mean PETC0 2 (p=0.25). The mean absolute change in PaC0 2 between control and the highest ventilation was 2.2 ± 1.8 mmHg (range 0.4 to 4.8) for /and 3.4 ± 2.3 mmHg (range 0.4 to 5.6) for VT. COMMENTARY The system minimized decreases in PETC0 2 over a wide range of ventilation (56 to 131 L min ) and breathing patterns, in hyperventilating human subjects and in mechanically hyperventilated dogs (4 to 12 L min ). The variability in PaC0 2 in the hyperventilated dogs, although small, may have been due to a) imprecise matching of reserve gas PC0 2 to the dog's PvC0 2 s; b) prolonged duration of the maneuver in dogs (> 15 min versus 3 min for human subjects) and c) the extent of hyperventilation (see below). In addition, the different levels of ventilation may have induced changes in systemic and pulmonary blood flow (ventilation-perfusion matching, physiological and anatomical dead space), thereby affecting PaC0 2 and PvC0 2 . Despite these sources of variability, the range over which PaC0 2 varied in my studies in dogs was similar to those reported in studies utilizing more complex equipment (see Table 1). Conventional servo-controlled techniques designed to prevent changes in PC0 2 with hyperpnea are less affected by changes in C0 2 production than the circuit; however, they have other limitations. The assumption that detected changes in PETC0 2 are due to a change in PaC0 2 is not always warranted (14). Small changes in ventilatory pattern can 'uncouple' PETC 0 2 from PaC0 2 , resulting in PETC 0 2 being an inappropriate input for the control of PaC0 2 . For example, a smaller VT decreases VA (which tends to increase PaC0 2 ) but will also decrease PETC0 2 , causing a servo-controller to respond with an inappropriate increase in inspired C0 2 . Even under ideal conditions, a servo-controlled system attempting to correct for changes in PETC0 2 cannot predict the size of an impending VT in a spontaneously breathing subject and thus deliver the appropriate C0 2 load. If in an attempt to obtain fine control the gain in a servo-control system is set too high, the response becomes unstable and may result in oscillation of the control variable (11). Conversely, if the gain is set too low, compensation lags (9). Over-damping of the signal results in a the response never reaching the target. To address these problems, servo-controllers require complex algorithms (16) and expensive equipment. When C0 2 production is constant, the circuit has the theoretical advantage over servo-controlled systems in that it provides passive compensation for changes in V. This minimizes changes in VA, preempting the need for subsequent compensation. Maintenance of a nearly constant VA occurs even during irregular breathing, including brief periods when V is less than the FGF. Under this circumstance, excess FGF is stored in the fresh gas reservoir and subsequently contributes to VA when ventilation exceeds FGF. When C0 2 production increases during hyperventilation, as would occur with increased work of breathing or exercise, my method requires modification. To compensate, additional VA can be provided either by increasing FGF or by lowering the PC0 2 of the reserve gas below the PvC0 2 , as expressed in the following equation: VA = FGF + (V-FGF) (PvC02 - reserve gas Pco 2 ) Because spontaneously breathing subjects had such variable V during hyperventilation, compensating for the C0 2 production by modifying FGF would have required constant adjustment. We therefore chose to decrease the PC0 2 of the reserve gas to establish a concentration gradient between the PC0 2 of the reserve gas and the PvC0 2 ; when this gradient is constant, VA is a function of V. We found that, over the wide range of V exhibited by the subjects, a concentration of 5.5% C0 2 in the reserve gas (instead of 6.5% which corresponds to a PvC0 2 of 46 mmHg) provided the optimal gradient to compensate for increases in C0 2 production resulting from increased work of breathing. I therefore have described a simple circuit that disassociates VA from V. It passively minimizes increases in VA that would normally accompany hyperventilation when C0 2 production is constant. It can be modified to compensate for increases in C0 2 production. The circuit may form the basis for a simple and inexpensive alternative to servo- controlled systems for research and may have therapeutic applications. TABLE π Dog # Weight Initial FETC0 2 Bag FC0 2 (kg) (%) (%) 1 22 5.3 7.0 2 20 4.6 6.6 3 20 7.1 9.0 4 24 7.3 9.0 5 25 5.5 6.9 20 6.0 7.2 TABLE III End Tidal PC0 2 (mmHg) Frequency (min- 1 ) Tidal Volume (L) Minute Ventilation (L- min 1 ) While the foregoing provides a detailed description of a preferred embodiment of the invention, it is to be understood that this description is illustrative only of the principles of the invention and not limitative. Furthermore, as many changes can be made to the invention without departing from the scope of the invention, it is intended that all material contained herein be interpreted as illustrative of the invention and not in a limiting sense.

Claims: THE EMBODIMENTS OF THE INVENTION IN WHICH AN EXCLUSIVE PROPERTY OR PRIVILEGE IS CLAIMED ARE AS FOLLOWS: 1. A breathing circuit and components thereof for causing the administration of carbon dioxide gas to the patient to maintain the same PC0 2 in the patient independent of the rate of ventilation (so long as the said rate of ventilation is greater than a control rate of ventilation). 2. The circuit of claim 1 wherein the circuit permits the rate of anaesthetic vapour elimination from the lungs of the patient to vary directly as the total ventilation by the patient, whether the patient is breathing normally or is hyperventilating. 3. The circuit of claim 1 wherein the circuit permits the rate of nitrogen elimination from the lungs of the patient to vary directly as the total ventilation by the patient, whether the patient is breathing normally or is hyperventilating. 4. A breathing circuit comprises components which together form the simple circuit and comprise (a) an exit port from which the gases exit from the circuit to the patient, (b) a non-rebreathing valve which constitutes a one-way valve permitting gases to be delivered to the exit port to be delivered to the patient but which non-breathing valve when the patient breathes into the exit port does not permit the gases to pass the nonrebreathing valve into the portion of the circuit from which the gases are delivered but passes them to ambient or elsewhere, (c) a source of gas (which may be oxygen or air or other gases but does not contain CO 2 in communication with the non-breathing valve to be delivered through the valve to the patient, (d) a fresh gas reservoir in communication with the source of fresh gas flow for receiving excess gas not breathed by the patient from the source of gas and for storing same and when the patient breathes and withdraws amounts of gas from the source of gas flow also enables the patient to receive gas from the fresh gas reservoir in which the gases have been stored, (e) a reserve gas supply containing CO 2 and other gases wherein the partial pressure of the CO 2 is approximately equal to the partial pressure of the CO 2 in the patient's mixed venous blood, for being delivered to the non-rebreathing valve as required by the patient to make up that amount of gas required by the patient when breathing that is not fulfilled from the gases delivered from the source of gas flow and fresh gas reservoir, the said source of gas and fresh gas reservoir and reserve gas supply being disposed on the side of the valve remote from the exit port. 5. The circuit of claim 4 further comprising a pressure relief valve is in communication with the fresh gas reservoir, in the event that the fresh gas reservoir overfills with gas so that the fresh gas reservoir does not break, rupture or become damaged in any way. 6. The circuit of claim 4 or 5 wherein the reserve gas supply includes a demand valve regulator so that where the additional gas is required, the demand valve regulator opens the communication of the reserve gas supply to the non-rebreathing valve for delivery of the gas to the non- breathing valve and where not required the demand valve regulator is closed and only fresh gas flows from the source of fresh gas and from the fresh gas reservoir to the non-rebreathing valve. 7. The use of the circuit of claim 1, 2, 3, 4, 5 or 6 is made in the manufacture of a device to hasten the recovery of patients from administration of vapour anaesthetics. 8. The use of the circuit of claim 1, 2, 3, 4, 5 or 6 to hasten the recovery of patients from vapour anaesthetics administration. 9. A method of treatment of an animal to recover from vapour anaesthetics administration, the method comprising delivering to a patient gases which do not contain CO 2 at a specified rate, and gases containing CO 2 to maintain the same PCO 2 in the animal independent of the rate of ventilation, at the rate of ventilation of the animal which exceeds the rate of administration of the gases which do not contain CO 2 . 10. The method of claim 9 wherein the animal is a person. 11. The method of claim 9 or 10 wherein the animal is enabled to recover from vapour anaesthetics administration, the method comprising delivering to a patient gases which do not contain CO 2 at a specified rate, and gases containing CO 2 to maintain the same PCO 2 in the animal independent of the rate of ventilation, at the rate of ventilation of the animal which exceeds the rate of administration of the gases which do not contain CO 2 .

Inventors: FISHER JOSEPH A, FISHER, JOSEPH, A.
Applicants: FISHER JOSEPH A, FISHER, JOSEPH, A.
Application year: 1997
Main classification: A61M16
IPC codes: A61M16