US20070169779A1

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Publication number: US20070169779A1
Application number: US11/339,307
Authority: US
Inventors: Gary Freeman
Original assignee: Zoll Medical Corp
Current assignee: Zoll Medical Corp
Priority date: 2006-01-24
Filing date: 2006-01-24
Publication date: 2007-07-26
Also published as: JP2013240702A; US20110120471A1; JP2007195977A; US20170056612A1; US9457165B2; CN101007195A; EP1810709B1; CN101007195B; JP5384795B2; JP5593427B2; EP1810709A1; US9950134B2

Abstract

An apparatus and method for resuscitating a patient suffering from cardiac arrest or another condition in which normal circulation has been interrupted. A ventilator is used for delivering a gas mixture to the patient. The ventilator is configured to adjust the partial pressure of CO2 to one or more partial pressures high enough to slow expiration of CO2 from the patient's lungs and thereby maintain a reduced pH in the patient's tissues for a period of time following return of spontaneous circulation.

Description

TECHNICAL FIELD

This invention relates to ventilatory support devices for use in cardiac arrest.

BACKGROUND

Cardiac Arrest, or Sudden Death, is a descriptor for a diverse collection of physiological abnormalities with a common cardiac aetiology, wherein the patient typically presents with the symptoms of pulselessness, apnoea, and unconsciousness. Cardiac arrest is widespread, with an estimated 300,000 victims annually in the U.S. alone and a similar estimate of additional victims worldwide. Early defibrillation is the major factor in sudden cardiac arrest survival. There are, in fact, very few cases of cardiac arrest victims saved which were not treated with defibrillation. There are many different classes of abnormal electrocardiographic (ECG) rhythms, some of which are treatable with defibrillation and some of which are not. The standard terminology for this is “shockable” and “non-shockable” ECG rhythms, respectively. Non-shockable ECG rhythms are further classified into hemodynamically stable and hemodynamically unstable rhythms. Hemodynamically unstable rhythms are those which are incapable of supporting a patient's survival with adequate blood flow (non-viable). For example, a normal sinus rhythm is considered non-shockable and is hemodynamically stable (viable). Some common ECG rhythms encountered during cardiac arrest that are both non-shockable and hemodynamically unstable are: bradycardia, idioventricular rhythms, pulseless electrical activity (PEA) and asystole. Bradycardias, during which the heart beats too slowly, are non-shockable and also possibly non-viable. If the patient is unconscious during bradycardia, it can be helpful to perform chest compressions until pacing becomes available. Idioventricular rhythms, in which the electrical activity that initiates myocardial contraction occurs in the ventricles but not the atria, can also be non-shockable and non-viable (usually, electrical patterns begin in the atria). Idioventricular rhythms typically result in slow heart rhythms of 30 or 40 beats per minute, often causing the patient to lose consciousness. The slow heart rhythm occurs because the ventricles ordinarily respond to the activity of the atria, but when the atria stop their electrical activity, a slower, backup rhythm occurs in the ventricles. Pulseless Electrical Activity (PEA), the result of electromechanical dissociation (EMD), in which there is the presence of rhythmic electrical activity in the heart but the absence of myocardial contractility, is non-shockable and non-viable and would require chest compressions as a first response. Asystole, in which there is neither electrical nor mechanical activity in the heart, cannot be successfully treated with defibrillation, as is also the case for the other non-shockable, non-viable rhythms. Pacing is recommended for asystole, and there are other treatment modalities that an advanced life support team can perform to assist such patients, e.g. intubation and drugs. The primary examples of shockable rhythms that can be successfully treated with defibrillation are ventricular fibrillation, ventricular tachycardia, and ventricular flutter.

Normally, electrochemical activity within a human heart causes the organ's muscle fibers to contract and relax in a synchronized manner. This synchronized action of the heart's musculature results in the effective pumping of blood from the ventricles to the body's vital organs. In the case of ventricular fibrillation (VF), however, abnormal electrical activity within the heart causes the individual muscle fibers to contract in an unsynchronized and chaotic way. As a result of this loss of synchronization, the heart loses its ability to effectively pump blood. Defibrillators produce a large current pulse that disrupts the chaotic electrical activity of the heart associated with ventricular fibrillation and provides the heart's electrochemical system with the opportunity to re-synchronize itself. Once organized electrical activity is restored, synchronized muscle contractions usually follow, leading to the restoration of effective cardiac pumping.

First described in humans in 1956 by Dr. Paul Zoll, transthoracic defibrillation has become the primary therapy for cardiac arrest, ventricular tachycardia (VT), and atrial fibrillation (AF). Monophasic waveforms dominated until 1996, when the first biphasic waveform became available for clinical use. Attempts have also been made to use multiple electrode systems to improve defibrillation efficacy. While biphasic waveforms and multiple-electrode systems have shown improved efficacy relative to monophasic defibrillation, there is still significant room for improvement: shock success rate for ventricular fibrillation (VF) remains less than 70% even with the most recent biphasic technology. In these cases, shock success was defined to be conversion of a shockable rhythm into a non-shockable rhythm, including those non-shockable rhythms which are also non-viable. Actual survival-to-hospital-discharge rates remain an abysmal ten percent or less. Survival rates from cardiac arrest remain as low as 1-3% in major U.S. cities, including those with extensive, advanced prehospital medical care infrastructures.

Approximately 40-50% of cardiac arrest victims are resuscitated by paramedics and emergency medical technicians (EMTs) in the field and brought to the hospital for further treatment; however, due to the insult on the victim's vital organs from the cardiac arrest, typically only about 25% (or approximately 40,000 out of 600,000 cardiac arrest victims, worldwide) of those victims who survive to the hospital will survive to being discharged from the hospital.

The treatment window for cardiac arrest with current treatments of defibrillation, cardiopulmonary resuscitation, and inotropic (e.g. epinephrine) drug treatment is very narrow. Long term survival rates from the time of victim collapse decrease at a roughly exponential rate with a time constant of roughly 2 minutes. Thus, just two minutes of delay in treatment using the currently recommended treatment protocols result in a long term survival rate of 30-35%. After 15 minutes, the long term survival rates are below 5%. While the response times of emergency medical systems have improved significantly over the last quarter century to the point that average times from emergency call to arrival at the victim is typically 9 minutes or less, bystander delays in making the emergency call typically add 2-3 minutes to the total arrest time, for a total of 11-12 minutes. In addition, the bystander making the emergency call may not even have witnessed the cardiac arrest, which may have occurred at some point in the past. Unwitnessed arrest accounts for at least half of all cardiac arrests. Cardiac arrest downtimes are only reported for witnessed arrests; it has been estimated, however, that if unwitnessed arrests were to be included, the average downtime for all victims would exceed 15 minutes. At the time of initial collapse, the ECGs of nearly all cardiac arrest victims are shockable rhythms such as VF or VT; after 15 minutes, however, the ECG rhythms of most cardiac arrest victims have degenerated into the non-shockable rhythms of PEA or asystole. Attempts to reduce this response time through the widespread adoption of AEDs has been minimally successful, at best, for a variety of economic and social factors. It would be thus advantageous to have treatment methods available to deal with cardiac arrest victims with profound ischemia due to long downtimes.

During cardiac arrest, cerebral blood flow ceases and global cerebral hypoxic-ischemic injury begins within minutes. Myocardial and neuronal tissue is able to remain viable during prolonged periods of ischemia—as long as twenty minutes, but paradoxically will sustain immediate damage during the return of circulation and oxygenation. It has been shown in a variety of studies at the tissue-level and animal model that successful resuscitation with return of spontaneous circulation (ROSC) leads to a secondary cascade of injury related to reperfusion injury. This reperfusion injury is particularly acute in neuronal tissue. When neurons and myocytes shift to anaerobic metabolism as a result of oxygen depletion, during the course of ATP hydrolysis lactate is converted to lactic acid, H+ is generated, and intracellular pH drops. This activates the sodium/hydrogen (NaH) exchange ion channels, which, however, require ATP and thus become depressed during ischemia. There is thus a build-up of intracellular H+ during ischemia. During reperfusion, the NaH exchange channel is reactivated causing a net influx of sodium which then causes a net influx of calcium via the sodium/calcium (NCX) exchange channel in order to exteriorize the elevated sodium ions. Elevation of intracellular calcium can lead to an accumulation of this ion by mitochondria, with activation of mitochondrial permeability transition (MPT).

During reperfusion, intracellular levels of glutamate, an excitatory neurotransmitter released from presynaptic terminals, increases markedly. Glutamate activates ion channel complexes, particularly the N-methyl-D-aspartate (NMDA) receptors, which when activated increase calcium conductance from the extracellular to intracellular fluid. Mitochondrial calcium increases, resulting in the formation of reactive oxygen species. Both mitochondrial calcium overload and ROS production initiate the formation of large pores in the mitochondrial membrane. Opening of high-conductance mitochondrial transition pores (MTP) in the mitochondrial inner membrane initiates onset of the mitochondrial permeability transition (MPT). The MTP pores conduct both positively and negatively charged solutes of up to 1,500 Da. Pore opening causes the collapse of mitochondrial membrane potential and cessation of mitochondrial ATP production. In addition, multiple biochemical cascades lead to the production of oxygen free-radicals and the activation of proteases, endonucleases, phospholipases and xanthine oxidase which cause destruction of cell membranes and other essential cytoskeletal structures such as microtubules. Even if these events are not immediately fatal to the cell, some neurons later undergo programmed cell death (apoptosis).

After successful cardiac resuscitation and ROSC, cerebral blood flow may remain abnormally low for several hours. After an initial hyperemia resulting from high circulating levels of catecholamines, cerebral blood flow decreases just as the cerebral metabolic rate for oxygen increases. This can lead to a prolonged state of relative cerebral ischemia. This prolonged mismatch between cerebral metabolic rate and blood flow, and ongoing biochemical and molecular processes related to delayed neuronal apoptotic and necrotic cell death, provide the scientific rationale for induced hypothermia as a form of neuroprotection after cardiac arrest. One method developed is the cooling of comatose cardiac arrest survivors to approximately 34 degrees Celsius within 4 hours of arrest onset. The exact mechanism for the therapeutic effects of hypothermia is not fully understood, but has been shown in several studies to enhance the survival rates of patients who are initially resuscitated (the approximately 40-50% of victims making it to the hospital). Hypothermia is common in the cardiac intensive care, hospital environment such as in bypass operations, etc, but there are two related drawbacks of hypothermia which have prevented its widespread use in the pre-hospital environment.

The first of these drawbacks is the primary biomedical engineering challenge of hypothermia: the large thermal mass of the victim and the difficulty of cooling the victim quickly and safely. While it has been shown that hypothermia is beneficial as long as it is applied within 4 hours of cardiac arrest, studies have also shown that cooling prior to resuscitation provides additive therapeutic benefits. While the causes for this are only speculative, one of the factors is likely the positive effects of hypothermia during the reperfusion phase of resuscitation. Practically speaking, it is highly undesirable to delay defibrillation and resuscitation to cool a patient to the proper temperature. Non-invasive methods of cooling take at minimum 10 minutes to 1 hour, while invasive methods such as extraction and cooling of the blood may take only 3-5 minutes, but are hazardous to the patient, particularly in the pre-hospital environment. In the case of defibrillation, even a delay of 3 minutes can result in a decrease in survival of 30%. While hypothermia may be effective at counteracting longer-term deleterious effects of ischemia and reperfusion, it would be desirable to have a treatment that can provide immediate protective effects against reperfusion injury while, at the same time, not delaying any current resuscitation interventions.

The mechanisms allowing prolonged cell survival during ischemia and minimizing lethal cell injury after reperfusion remain incompletely understood. It has been shown in studies that the naturally occurring acidosis of ischemia, like hypothermia, strongly protects renal cells, myocytes, and hepatocytes against ischemia-induced cell death. In contrast, the return of extracellular pH to physiological levels is an event that actually precipitates lethal cell injury, termed the “pH paradox”. It has been hypothesized by researchers that the pH dependency of reperfusion injury may be the consequence of the pH dependency of the MTP opening. Conductance of the NMDA channel is also known to decrease steeply when extracellular pH is reduced below 7.0. Intracellular pH may also be important; intracellular acidosis during and after simulated ischemia and reperfusion has been shown to protect cultured cardiac myocytes against injury. Increased extracellular proton concentration will also minimize the inward sodium influx via the Na-H exchange ion channels, thereby reducing the intracellular sodium concentrations and the net influx of calcium via the sodium-calcium exchanger channels, and thus minimizing calcium overload.

Ventilation is a key component of cardiopulmonary resuscitation during treatment of cardiac arrest. Venous blood returns to the heart from the muscles and organs depleted of oxygen (O₂) and full of carbon dioxide (CO₂). 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 sum 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 CO₂(PCO₂) in the mixed venous blood (PvCO₂) and the alveolar PCO₂. The C0₂diffuses into the alveoli from the mixed venous blood from the beginning of inspiration until an equilibrium is reached between the PvCO₂and the alveolar PCO₂at some time during the breath. When the subject exhales, the first gas that is exhaled comes from the trachea and major bronchi which do not allow gas exchange and therefore will have a gas composition similar to the inhaled gas. The gas at the end of this exhalation is considered to have come from the alveoli and reflects the equilibrium CO₂concentration between the capillaries and the alveoli; the PCO₂in this gas is called end-tidal PCO₂(PE_tCO₂).

When the blood passes the alveoli and is pumped by the heart to the arteries it is known as the arterial PCO₂(PaCO₂). The arterial blood has a PCO₂equal to the PCO₂at equilibrium between the capillaries and the alveoli. With each breath some CO₂is eliminated from the lung and fresh air containing little or no CO₂(CO₂concentration is assumed to be 0) is inhaled and dilutes the residual alveolar PCO₂, establishing a new gradient for CO₂to diffuse out of the mixed venous blood into the alveoli. The rate of breathing, or minute ventilation (V), usually expressed in L/min, is exactly that required to eliminate the CO₂brought to the lungs and maintain an equilibrium PCO₂(and PaCO₂) of approximately 40 mmHg (in normal humans). When one produces more CO₂(e.g., as a result of fever or exercise), more CO₂is produced and carried to the lungs. One then has to breathe harder (hyperventilate) to wash out the extra CO₂from the alveoli, and thus maintain the same equilibrium PaCO₂. But if the CO₂production stays normal, and one hyperventilates, then the PaCO₂falls. Conversely, if CO₂production stays constant and ventilation falls, arterial PCO₂rises. Some portion of the inspired air volume goes to the air passages (trachea and major bronchi) and alveoli with little blood perfusing them, and thus doesn't contribute to removal of CO₂during exhalation. This portion is termed “dead space” gas. That portion of V that goes to well-perfuised alveoli and participates in gas exchange is called the alveolar ventilation (VA) and exhaled gas that had participated in gas exchange in the alveoli is termed “alveolar gas”.

Monitoring and control of ventilation parameters as a function of measured expiratory CO₂is commonly used in ventilation systems. U.S. Pat. No. 4,112,938 describes a respirator that uses measurement of alveolar gas CO₂partial pressure as a means of adjusting a reservoir size to control inspiratory CO₂concentration. U.S. Pat. No. 5,320,093 describes a ventilator that adjusts inspiratory CO₂concentration so as to enhance a patient's natural ventilatory drive during recovery from anesthesia. In U.S. Pat. No. 5,402,796, a method is described which provides better accuracy of PaCO₂utilizing an initial calibration sample. U.S. Pat. Nos. 5,778,872, 6,612,308B2 and 6,799,570B2 portable ventilators that use reservoirs to store exhaled air for later use in rebreathing during inspiration so as to keep CO₂levels constant (“isocapnia”). U.S. Pat. No. 6,612,308B2 is further refined in No. 6,622,725B1 by providing a method for separating out the alveolar gas from the dead space gas, thus concentrating the expiratory CO₂for later rebreathing. U.S. Pat. No. 6,951,216B2 describes a ventilator utilizing a space-efficient CO₂exchanger that absorbs and stores expiratory CO₂gas that is later released into the inpsiratory gas stream to enhance CO₂concentrations.

SUMMARY

In general, the invention features an apparatus and method for resuscitating a patient suffering from cardiac arrest or another condition in which normal circulation has been interrupted. A ventilator is used for delivering a gas mixture to the patient. The ventilator is configured to adjust the partial pressure of CO2 to one or more partial pressures high enough to slow expiration of CO2 from the patient's lungs and thereby maintain a reduced pH in the patient's tissues for a period of time following return of spontaneous circulation.

Other features and advantages of the invention will be apparent from the description and drawings, and from the claims.

DESCRIPTION OF DRAWINGS

FIG. 1 is the system block diagram of one implementation of one aspect of the invention, including a ventilator integrated with a mechanical chest compression device and a defibrillator.

FIG. 2 is a block diagram of the ventilator ifFIG. 1.

FIGS. 3A and 3B are plots depicting a typical end-tidal capnographic measurement curve.

FIGS. 4A and 4B are plots depicting the end-tidal capnographic curve (dotted line) with elevated levels of inspired CO₂.

FIG. 5 is a block diagram of a gas mixture control loop of the implementation ofFIG. 1.

DETAILED DESCRIPTION

There are a great many different implementations of the invention possible, too many to possibly describe herein. Some possible implementations that are presently preferred are described below. It cannot be emphasized too strongly, however, that these are descriptions of implementations of the invention, and not descriptions of the invention, which is not limited to the detailed implementations described in this section but is described in broader terms in the claims.

Some implementations may reduce reperfusion injury by maintaining a low tissue pH during the time period immediately prior to and from 0-60 minutes subsequent to the return of spontaneous circulation (ROSC) by means of addition of carbon dioxide to the inspiratory gases while at the same time increasing oxygen content relative to normal room air concentrations to enhance oxygenation of the brain, heart and other vital organs.

Referring toFIGS. 1 and 2, the block diagram inFIG. 1 shows an integrated resuscitation system (IRS) with components designed to address various aspects of a resuscitation:defibrillator13,mechanical compressor12, andventilator15. By control of the partial pressures of the ventilation gases (particularly oxygen), ambient air, and carbon dioxide via the mixingvalves35, the IRS can maintain a patient's tissue pH at approximately the below normal level present immediately prior to ROSC.

The tissue pH is controlled by the following well known physiological mechanism. The transport of CO₂can have a significant impact on the acid-base status of the blood and tissues. The lung excretes over 10,000 molar equivalents of carbonic acid per day compared to less than 100 molar equivalent of fixed acids by the kidneys. Therefore, by altering alveolar ventilation and the elimination of CO₂, the acidity of the tissues of the brain, heart, gut and other organs can be modified. CO₂is carried in the blood in three forms: dissolved, as bicarbonate, and in combination with proteins such as carbamino compounds. In solution, carbon dioxide hydrates to form carbonic acid:
CO₂+H₂O
H₂CO₃
The largest fraction of carbon dioxide in the blood is in the form of bicarbonate ion, which is formed by ionization of carbonic acid:
H₂CO₃
H⁺+HCO₃
2H⁺+CO₃²⁻
Using the law of mass action, the Henderson-Hasselbalch equation is derived:
[H⁺]=K₁⁻[H₂CO₃]/[HCO₃³¹], or
[H+]=K⁻(αP_CO2)/[HCO₃⁻],
where α P_CO2is the total concentration of CO₂and H₂CO₃. The log form of the Hasselbalch equation takes the form:
pH=pK_A+log (HCO₃⁻)/(0.03 P_CO2),
where K_Ais the dissociation constant of carbonic acid, equal to 6.1.
Normal HCO₃⁻ concentration is 24 mmol/liter, with a resultant pH of 7.4. During total ischemia induced by cardiac arrest or trauma, pH will fall to below 7, and commonly in the range of 6.5-6.8, as a result of increasing levels of CO₂. At the resumption of circulation and gas exchange in the alveoli, the end-tidal carbon dioxide (E_tCO₂) value, as measured by the commonly used capnograph or capnometer, increases rapidly from a value typically below 10 mmHg found during arrest to a supranormal value of 50-75 mmHg—normal values are approximately 35 mmHg—as the body attempts to reduce its CO₂levels.
Referring toFIGS. 3A and 3B, phase I represents airway dead space. It is the CO₂-free portion of the exhaled breath from the conducting airways. Phase II represents the mixing of airway dead space gas with alveolar gas and is characterized by a significant rise in CO₂. Phase III represents alveolar volume. The plateau reflects the level of effective ventilation in the alveoli. Two lines are constructed on the graph; one on the slope of Phase III and the other such that areas p and q are equal.
Airway dead space is measured from the start of expiration to the point where the vertical line crosses the exhaled volume axis. The volume of CO₂in the breath is equal to area X, the total area under the curve. Adding individual breath volumes allows minute CO₂elimination to be calculated in ml/min. Physiologic Vd/Vt as well as physiologic and alveolar dead space can also be calculated if arterial PCO₂is known. A line representing the arterial PCO₂value is constructed parallel to the exhaled volume axis creating areas Y and Z. Area X represents the volume of CO₂in the exhaled tidal volume. Areas Y and Z represent wasted ventilation due to alveolar and airway dead space respectively.
Referring toFIGS. 1, 4A and4B, and the flowchart inFIG. 5, theprocessing unit14, made up of an electronic processor such as a microprocessor as well as memory and support logic, first determines that a cardiac arrest is in progress, by one or a combination of such known techniques as: (1) electrocardiographic (ECG) analysis to determine whether the ECG is a rhythm due to ventricular fibrillation, ventricular tachycardia, PEA or asystole or a rhythm of supraventricular origin such as a normal sinus rhythm; (2) analysis of the transthoracic impedance signal to determine whether there is blood flow; or (3) simply by means of an input via theuser interface6 by therescuer4 indicating that an arrest is in progress. If an arrest is determined to be in progress, the inspiratory gas mixture is adjusted via electronically-controlledflow valves35 in the differential flow control (DFC) subunit to be predominantly oxygen (60-100%). Once in the CARDIAC ARREST state, theprocessing unit14 will wait for input that defines ROSC. This input may be as simple as an input via the user interface by the rescuer that ROSC has occurred, though preferably the input includes a capnometric signal measuring end tidal CO₂(E_tCO₂) values2 in the expired air. When theprocessing unit14 detects an increase of more than 30% of the baseline cardiac arrest E_tCO₂value in30 seconds and a value greater than 25 mmHg, theprocessing unit14 will enter the ROSC state, and begin the process of adding CO₂to the inspired gas mixture.
In some implementations, the desired partial gas pressure of CO₂in the inspired gas mixture is solely a function of the E_tCO₂value. The first ventilation will have the flow ratios of oxygen, room air and CO₂set such that the CO₂partial pressure (CO_2i) is 90% of the E_tCO₂value (CO_2i^L). Theprocessing unit14 then checks the E_tCO₂value of the subsequent exhalation to verify that the end tidal value is higher than the CO_2i; if so, the next CO_2iis set to 110% of the most recent E_tCO₂. If the E_tCO₂is not found to be higher than the CO_2i, then the partial pressure of CO₂in the next ventilation is reduced by 10%. If, after three such cycles where the E_tCO₂is not found to be higher than the CO_2i, then the CO_2iis reduced to zero to get a baseline level for expired CO₂. If, on the ventilation cycle where the CO_2iwas set to 110% of the E_tCO₂value (CO_2i^H), the E_tCO₂value of the subsequent exhalation is not lower than the CO_2i^Hthen the partial pressure of CO₂for the next ventilation cycle will be increased a further 10%.
Referring toFIG. 2, the ventilator provides for both negative and positive pressures by means of thedouble venturi32 such as that described in U.S. Pat. No. 5,664,563. Safety mechanisms are provided byshutoff valve31 andexhaust valve28. Heater/humidifier element33 conditions the gas prior to entering the inspiration circuit, and capnometric measurements are determined using thecapnometric sensor22 andtidal volume sensor21.
Referring again toFIGS. 3A and 3B, by measuring both flow rates and the CO₂concentration (partial pressure), the quantity of CO₂for the inspiration and expiration cycle can be tracked by integrating the CO₂flow. Though the amount of excess CO₂may be unknown, the amount of CO₂transferred from the bloodstream to the alveoli can be accurately controlled by measuring the difference in CO₂volume on the inspired and expired cycles. Thus to achieve constant CO₂levels, CO_2iis increased to the level such that the volumes of CO₂on inspired and expired cycles are equal. Volumetric measurements for the inspired and expired cycles may be averaged over several cycles to increase accuracy.
In other implementations, either the tissue CO₂or pH are measured by such methods as disclosed in U.S. Pat. 6,055,447, which describes a sublingual tissue CO₂sensor, or U.S. Pat. Nos. 5,813,403, 6,564,088, and 6,766,188, which describe a method and device for measuring tissue pH via near infrared spectroscopy (NIRS). NIRS technology allows the simultaneous measurement of tissue PO₂, PCO₂, and pH. One drawback of previous methods for the measurement of tissue pH is that the measurements provided excellent relative accuracy for a given baseline measurement performed in a series of measurements over the course of a resuscitation, but absolute accuracy was not as good, as a result of patient-specific offsets such as skin pigment. One of the benefits of the currently-described implementations is that they do not require absolute accuracy of these pH measurements, only that the offset and gain be stable over the course of the resuscitation. Because tissue pH responds slowly over the course of multiple ventilation cycles, it is used primarily to augment control of E_tCO₂levels by adjusting CO_2iwith the goal of regulating tissue pH per the following regimen: (1) during the first 5 minutes following ROSC, the pH should remain flat; (2) during the time period of 5-10 minutes, the tissue pH should increase no more than 0.4 pH units/minute, and should be limited to not increase above an absolute number of 6.8; and (3) during the 10-15 minute time period, if the pH is still less than 6.8, CO_2iis adjusted to allow pH to increase at a rate of approximately 0.4 pH units/minute, and if tissue pH is greater than 7 then CO_2iis adjusted to a slower rate of 0.2 pH units/minute.
In some cases, such as cardiac arrest cases with shorter periods of ischemia, it may be desirable to reduce pH levels below the levels present in the cardiac arrest victim by augmenting CO₂levels. In such cases, pH would be decreased duringphase1 of the regimen described in the previous paragraph.
Tissue CO₂, and thus pH, as well, are adjusted by increasing or decreasing inspired CO₂levels via the CO_2i^Hand CO_2i^Llevels; for instance, decreasing both levels will cause additional CO₂to be exhaled, thus reducing tissue pH. Adjustments are made in approximately 10% increments at approximately 3 times per minute. The low update rate of CO_2i^Hand CO_2i^Llevels is due to the fact that the time constant for pH changes due to CO_2ichanges is slow as well.
In other implementations, medical knowledge such as that described in Crit Care Med 2000 Vol. 28, No. 1 (Suppl.) is incorporated into a closed loop feedback system to augment the methods described above for controlling tissue pH during resuscitation. As the author describes, the system of differential equations has been described in a number of publications. In this specific instance, “the human circulation is represented by seven compliant chambers, connected by resistances through which blood may flow. The compliances correspond to the thoracic aorta, abdominal aorta, superior vena cava and right heart, abdominal and lower extremity veins, carotid arteries, and jugular veins. In addition, the chest compartment contains a pump representing the pulmonary vascular and left heart compliances. This pump may be configured to function either as a heart-like cardiac pump, in which applied pressure squeezes blood from the heart itself through the aortic valve, or as a global thoracic pressure pump, in which applied pressure squeezes blood from the pulmonary vascular bed, through the left heart, and into the periphery. Values for physiologic variables describing a textbook normal ‘70-kg man’ are used to specify compliances and resistances in the model. The distribution of vascular conductances (1/resistances) into cranial, thoracic, and caudal components reflects textbook distributions of cardiac output to various body regions.” In addition to these equations, implementations may incorporate inspiratory volumetric measurement and the universal alveolar airway equation, the Henderson-Hasselbalch equation, and a three-compartment model of carbon dioxide storage in the body. The compartment with the lowest time constant corresponds to the well-perfused organs of brain, blood, kidneys, heart; the second compartment corresponds to skeletal muscle; and the third compartment corresponds to all other tissue.
Referring toFIG. 5, a closed loop feedback method is employed, using state space methods with thesystem estimation block55 provided by a physiological model as described above with augmentations to include CO₂and pH effects. TheFeedback Controller53 may employ such traditional control system methods as proportional, difference, integral (PID) or state feedback control methods, known to those skilled in the art.
Since the caiac arrest victim is spontaneously breathing during ROSC, and the central chemoreceptors will be stimulated by the elevated CO₂levels and depressed pH, it is necessary for the ventilator to respond to the victim's own inspiratory efforts. Pressure sensing is used to determine patient respiratory effort. A combination of synchronized intermittent mandatory ventilation (SIMV) and inspiratory pressure support ventilation (PSV) are used to provide proper responsiveness to victim respiratory needs while at the same time providing a sufficient amount of minute ventilation so that pCO₂can be regulated via CO_2i. SIMV allows the victim to take breaths between artificial breaths and PSV assists the victim in making an inspiration of a pattern that is largely of their own control. With PSV, the amount of support is variable, with more support being provided in the early stages of ROSC and the support gradually reduced as the victim's status improves during the course of ROSC.
Thedrug infuser14 may be used to deliver other agents such as glutamate, aspartate or other metabolically active agents that may be particularly effective during the pH-depressed reperfusion state of the invention in renormalizing lactate levels and generating the ATP stores necessary to restore cytosolic calcium homeostasis prior to allowing pH to increase.
Thechest compressor12 andventilator15 may be physically separate from the defibrillator, and thephysiological monitor10 and control of thechest compressor12 andventilator15 may be accomplished by acommunications link16. The communications link16 may take the form of a cable connecting the devices but preferably thelink16 is via a wireless protocol such as Bluetooth or a wireless network protocol such as Institute of Electrical and Electronics Engineers (IEEE) 802.11. Theseparate chest compressor12 can be a portable chest compression device such as that commercially available as the Autopulse™, provided by ZOLL Circulatory Systems of Sunnyvale, Calif. Theseparate ventilator15 can be a ventilator such as that is commercially available as the iVent™, provided by Versamed of Pearl River, N.Y. Theseparate drug infuser14 can be a drug infusion device such as that commercially available as the Power Infuser™, provided by Infusion Dynamics of Plymouth Meeting, Pa., or the Colleague CX™, provided by Baxter Healthcare Corp., of Round Lake, Ill. Thechest compressor12,ventilator15,drug infuser14 anddefibrillator13 can also be integrated into one housing such as that for the Autopulse™, provided by ZOLL Circulatory Systems of Sunnyvale, Calif.
In other implementations, control and coordination for the overall resuscitation event and the delivery of the various therapies may be accomplished by adevice17 or processing element external to either the chest compressor, ventilator, or defibrillator. For instance thedevice17 may be a laptop computer or other handheld computer or a dedicated computing device that will download and process the ECG data from the defibrillator, analyze the ECG signals, perform the determinations based on the analysis, and control the other therapeutic devices, including thedefibrillator13. While the system has been described for cardiac arrest, it is also applicable for trauma victims or other forms of arrest where the victim is suffering, from amongst other conditions, a global ischemia, and resuscitation from which requires the patient to transition through a state of reperfusion.
Many other implementations of the invention other than those described above are within the invention, which is defined by the following claims. References to “processing” in the claims include a microprocessor (and associated memory and hardware) executing software.

Claims

1. Resuscitation apparatus for resuscitating a patient suffering from cardiac arrest or another condition in which normal circulation has been interrupted, the apparatus comprising:

a ventilator for delivering a gas mixture to the patient,

wherein the ventilator includes apparatus configured to adjust the partial pressure of CO₂to one or more partial pressures high enough to slow expiration of CO₂from the patient's lungs and thereby maintain a reduced pH in the patient's tissues for a period of time following return of spontaneous circulation.

2. The apparatus ofclaim 1 wherein the partial pressure of CO₂is adjusted to be higher than ambient CO₂partial pressure during the period of time.

3. The apparatus ofclaim 1 wherein adjustment of the partial pressure of CO₂includes adding CO₂to the gas inspired by the patient.

4. The apparatus ofclaim 1 further comprising a sensor and associated processing for measuring a physiological status of the patient, wherein the partial pressure of CO₂is adjusted at least in part in response to the output of the sensor.

5. The apparatus ofclaim 4 wherein the sensor and associated processing are configured to detect return of spontaneous circulation, and wherein the partial pressure of CO₂is changed in response to detection of return of spontaneous circulation.

6. The apparatus ofclaim 1 wherein the period of time is greater than 30 seconds.

7. The apparatus ofclaim 6 wherein the period of time is greater than 3 minutes.

8. The apparatus ofclaim 5 wherein the sensor comprises a CO₂sensor.

9. The apparatus ofclaim 1 wherein adjustment of the partial pressure of CO₂has the effect of maintaining the pH of the patient's tissues below 7.0 for the period of time following return of spontaneous circulation.

10. The apparatus ofclaim 9 wherein the pH of the patient's tissues is maintained below 6.8.

11. The apparatus ofclaim 10 wherein the pH of the patient's tissues is maintained below 6.5.

12. The apparatus ofclaim 1 further comprising a defibrillator.

13. The apparatus ofclaim 1 further comprising a chest compressor.

14. The apparatus ofclaim 1 further comprising an infuser.

15. The apparatus ofclaim 1 further comprising a sensor and associated processing for determining the pH of the patient's tissue, wherein the partial pressure of CO₂is adjusted at least in part in response to the pH of the patient's tissue.

16. The apparatus ofclaim 15 wherein the partial pressure of CO₂is adjusted to maintain tissue pH below6.8 for a period of time following return of spontaneous circulation.

17. The apparatus ofclaim 1 wherein the partial pressure of CO₂is gradually lowered over at least a portion of the period of time so as to gradually raise the pH of the patient's tissues.

18. The apparatus ofclaim 1 further comprising processing using a mathematical model of the relationship between CO₂retention in the patient and the pH of the patient's tissues.

19. The apparatus ofclaim 18 wherein the mathematical model comprises processing using the Henderson-Hasselbalch equations.

20. The apparatus ofclaim 1 further comprising apparatus and processing for measuring the inspired volume and expired volume of CO₂in the ventilation cycle, and using the inspired and expired volumes to adjust the partial pressure of CO₂.

21. The apparatus ofclaim 1 further comprising apparatus and processing for monitoring an E_tCO₂level, and wherein the partial pressure of CO₂is adjusted to maintain the E_tCO₂level above a level found in the arrest victim prior to the arrest.

22. The apparatus ofclaim 21 wherein the adjustment of the partial pressure of CO₂is accomplished by adjusting the partial pressure between a lower level in a first cycle and a higher level in a second cycle, wherein in the first cycle the partial pressure of CO₂is lower than a previously measured E_tCO₂level, and wherein in the second cycle the partial pressure of CO₂is higher than the previously measured E_tCO₂level, and wherein the lower and higher levels are adjusted to maintain E_tCO₂at a desired level.

23. The apparatus ofclaim 13 wherein the ventilator and chest compressor are controlled so that a ratio of chest compression rate to ventilation rate is less than 15:2 during at least a portion of the period of time following return of spontaneous circulation.

24. The apparatus ofclaim 23 wherein the ratio is less than 5:1.

25. The apparatus ofclaim 24 wherein the ratio is about 6:2.

26. The apparatus ofclaim 1 further comprising a fluid infusion device.

27. The apparatus ofclaim 26 wherein the fluid infusion device is configured to infuse fluids containing metabolic substances during reperfusion.

28. The apparatus ofclaim 27 wherein the metabolic substances comprise amino acids.

29. The apparatus ofclaim 28 wherein the amino acids comprise aspartate, dihydroxyacetone phosphate or glutamate.

30. The apparatus ofclaim 1 further comprising a defibrillator, compressor, and infuser.

31. The apparatus ofclaim 30 wherein the defibrillator, compressor, ventilator, and infuserare separate devices and are linked by a communications link.

32. The apparatus ofclaim 31 wherein an additional computing device is used to synchronize all of the separate devices.

33. The apparatus ofclaim 1 wherein there are both negative and positive pressures available from the ventilator.

34. The apparatus ofclaim 1 wherein the ventilator is configured to elevate oxygen levels to greater than 40%.

35. The apparatus ofclaim 1 wherein the period of time begins prior to the return of spontaneous circulation.

36. The apparatus ofclaim 35 wherein the period of time begins immediately prior to the return of spontaneous circulation.

37. A method of resuscitating a patient suffering from cardiac arrest or another condition in which normal circulation has been interrupted, the method comprising:

applying a ventilator to the patient;

delivering a gas mixture to the patient using the ventilator,

wherein the ventilator is configured to adjust the partial pressure of CO₂to one or more partial pressures high enough to slow expiration of CO2 from the patient's lungs and thereby maintain a reduced pH in the patient's tissues for a period of time following return of spontaneous circulation.

38. The method ofclaim 37 wherein the partial pressure of CO₂is adjusted to be higher than ambient CO₂partial pressure during the period of time.

39. The method ofclaim 37 wherein adjustment of the partial pressure of CO₂includes adding CO₂to the gas inspired by the patient.

40. The method ofclaim 37 further comprising providing a sensor and associated processing for measuring a physiological status of the patient, wherein the partial pressure of CO₂is adjusted at least in part in response to the output of the sensor.

41. The method ofclaim 40 wherein the sensor and associated processing are configured to detect return of spontaneous circulation, and wherein the partial pressure of CO₂is changed in response to detection of return of spontaneous circulation.

42. The method ofclaim 37 wherein adjustment of the partial pressure of CO₂has the effect of maintaining the pH of the patient's tissues below 7.0 for the period of time following return of spontaneous circulation.

43. The method ofclaim 37 further comprising using a sensor and associated processing for determining the pH of the patient's tissue, and adjusting the partial pressure of CO₂at least in part in response to the pH of the patient's tissue.

44. The method ofclaim 37 wherein the period of time begins prior to the return of spontaneous circulation.