Average volume ventilation

Abstract

A ventilator supplies a plurality of volumes of fluid to a patient during a like plurality of inhalations by the patient. Each volume of fluid is supplied at an inspiratory positive airway pressure during a corresponding inhalation by the patient. A volume of fluid received by the patient is determined for each of the plurality of inhalations by the patient and an average volume of fluid received by the patient during each of the plurality of inhalations is determined. The average volume of fluid received by the patient during each inhalation is compared to a predetermined target volume and the inspiratory positive airway pressure each volume of fluid is supplied to the patient is adjusted as a function of the comparison.

Description

BACKGROUND OF THE INVENTION

[0002] 1. Field of the Invention

[0003] The present invention pertains to a ventilator and a method of controlling a ventilator to supply a desired inspiratory target volume of fluid, such as air or an oxygen mixture, to a patient.

[0004] 2. Description of the Related Art

[0005] It is known to utilize a conventional ventilator to deliver a fluid, such as air or an oxygen mixture, to a patient in a volume targeted ventilation mode in which the ventilator attempts to deliver to the patient, during inspiration, a preset volume of fluid. To adjust the volume of fluid delivered to the patient during inspiration to achieve this target volume during each inspiration, the ventilator adjusts the pressure of the fluid supplied to the patient. For example, for a given inspiratory phase in a plurality of respiratory cycles, increasing or decreasing the pressure increases or decreases the volume of fluid delivered to the patient, respectively.

[0006] Volume ventilators that operate in a volume targeted ventilation (“VTV”) mode monitor the actual volume of fluid delivered to the patient during an inhalation and increase or decrease, as needed, the pressure at which the fluid is delivered to the patient to meet a target volume of fluid. A problem with adjusting the volume of fluid delivered for one inhalation based upon a difference between the volume of fluid delivered during a previous inhalation and the target volume of fluid is that large differences between the previous volume and the target volume can result in large changes in the volume of fluid delivered to the patient. Such changes can result in the patient experiencing uncomfortable and unnatural variations in the volume of fluid received from one inhalation to another.

[0007] It is also known to operate a ventilator in a volume assured pressure support (“VAPS”) mode in which the pressure is controlled by the ventilator in a manner so as to ensure that a set minimum volume is always delivered to the patient during each breath. In this mode of volume ventilation, if, during an inspiratory phase, the patient's inspiratory flow is not sufficient to provide the set volume for that breath, the ventilator transitions to a volume controlled mode of operation and increases the pressure of the fluid flow to the patient to meet this set volume. This typically occurs at the middle or near the end of the inspiratory phase when the ventilator determines that the patient's inspiratory rate will not be sufficient to achieve the set volume for that breath. Because this increase in pressure typically occurs near the end of the breath, when the patient is most likely to want to exhale, this mode of ventilation can be uncomfortable to the spontaneously breathing patient.

SUMMARY OF THE INVENTION

[0008] Accordingly, it is an object of the present invention to provide a ventilator and method of controlling a ventilator that overcomes the shortcomings of conventional ventilators and conventional modes of ventilation. This object is achieved according one embodiment of the present invention by providing a method for adjusting a volume of fluid supplied to a patient from one inhalation to the next in a manner that is comfortable for the patient and responsive to the patient's changing respiratory demands. This method includes supplying a plurality of volumes of fluid to a patient during a like plurality of inspiratory phases of the patient. Each volume of fluid is supplied at an inspiratory positive airway pressure (“IPAP”) during a corresponding inspiratory phase, which is either triggered by the patient or by the ventilator. For each inspiratory phase, a volume of fluid received by the patient is determined. An average volume of fluid received by the patient is determined by taking an average of the volumes of fluid received by the patient during the plurality of inspiratory phases. The average volume of fluid received by the patient is compared to a predetermined target volume and the inspiratory positive airway pressure is adjusted based on this comparison.

[0009] In a further embodiment of the present invention determining the volume of fluid received by the patient for each inspiratory phase includes determining an estimated leak volume of fluid for each inspiratory phase. For each inspiratory phase, the estimated leak volume of fluid is subtracted from the supplied volume of fluid to obtain the volume of fluid received by the patient.

[0010] In an exemplary embodiment of the present invention, adjusting the inspiratory positive airway pressure based on the comparison between the average volume of fluid received by the patient and a predetermined target volume includes increasing the inspiratory positive airway pressure or decreasing the inspiratory positive airway pressure when the average volume is less than or greater than the predetermined target volume, respectively. Adjusting the inspiratory positive airway pressure based on this comparison can also include maintaining the inspiratory positive airway pressure when the average volume is within an offset volume of the predetermined target volume. The present invention also contemplates adjusting the pressure support based on the result of this comparison, which is done by adjusting the inspiratory positive airway pressure or the expiratory positive airway pressure (“EPAP”).

[0011] It is a further object of the present invention to provide a method of supplying a desired volume of fluid to a patient. This method includes supplying a first volume of fluid to the patient at a first inspiratory positive airway pressure. A first volume of fluid received by the patient is determined for the first volume of fluid supplied to the patient. A second volume of fluid is supplied to the patient at the first inspiratory positive airway pressure. A second volume of fluid received by the patient is determined for the second volume of fluid supplied to the patient. A first average volume of fluid received by the patient is determined from the first and second volumes of fluid received by the patient. The first average volume of fluid is compared to a predetermined target volume and the first inspiratory positive airway pressure is adjusted to a second inspiratory positive airway pressure as a function of the comparison.

[0012] This above-described method can also include supplying a third volume of fluid to the patient at the second inspiratory positive airway pressure and determining a third volume of fluid received by the patient for the third volume of fluid supplied to the patient. A second average volume of fluid received by the patient is determined as a function of the second and third volumes of fluid received by the patient. The second average volume is compared to the predetermined target volume and the second inspiratory positive airway pressure is adjusted to a third inspiratory positive airway pressure as a function of the comparison.

[0013] At least two of the first, second, and third inspiratory positive airway pressures can be the same. The second inspiratory positive airway pressure is greater than the first inspiratory positive airway pressure when the first average volume is less than the predetermined target volume. The second inspiratory positive airway pressure is less than the first inspiratory positive airway pressure when the first average volume is greater than the predetermined target volume. The second inspiratory positive airway pressure is the same as the first inspiratory positive airway pressure when the first average volume is within a predetermined offset volume of the predetermined target volume. At least one of the first volume of fluid and the second volume of fluid received by the patient can be determined using regression analysis.

[0014] The above object of providing a ventilator that overcomes the shortcomings of conventional ventilators is accomplished according to one embodiment of the present invention by providing an apparatus for supplying fluid to a patient that includes a pressure generating system that provides a flow of fluid, also referred to as “breathing gas”, at a variable pressure or a variable flow. A patient circuit operatively coupled to the pressure generating system delivers the flow of fluid to a patient. An interface device coupled to the patient circuit communicates the flow of fluid to the airway of the patient. A least one sensor in the apparatus detects a parameter indicative of a volume of fluid delivered to the patient. In addition, a controller receives signals from the sensor and controls the pressure generating system. In particular, the controller (a) determines, for each inspiratory phase of a respiratory cycle of the patient, a volume of fluid received by the patient based on the parameter indicative of a volume of fluid delivered to the patient provided by the sensor, (b) determines an average volume of fluid received by the patient over a plurality of inspiratory phases, (c) compares the average volume of fluid received by the patient to a predetermined target volume, and (d) causes the pressure generating system to adjust the pressure or the rate of flow of fluid output thereby based on this comparison.

[0015] The above object of providing a ventilator that overcomes the shortcomings of conventional ventilators is accomplished according to another embodiment of present invention by providing an apparatus for supplying fluid to a patient that includes a system for supplying a plurality of volumes of fluid to a patient during a like plurality of inspiratory phases of the patient's respiratory cycles, with each volume of fluid supplied at an inspiratory positive airway pressure during a corresponding inspiratory phase. A system that determines, for each inspiratory phase, a volume of fluid received by the patient. A system that determines an average volume of fluid received by the patient from the volumes of fluid received by the patient during the plurality of inspiratory phases. A system for comparing the average volume to a predetermined target volume, and a system that adjusts the inspiratory positive airway pressure based on this comparison.

[0016] The above object of providing a ventilator that overcomes the shortcomings of conventional ventilators is accomplished according to yet another embodiment of present invention by providing an apparatus for supplying fluid to a patient that includes a system for supplying a first volume of fluid to a patient at a first inspiratory positive airway pressure, and a system for determining, for the first volume of fluid supplied to the patient, a first volume of fluid received by the patient. The supply system supplies a second volume of fluid to the patient at the first inspiratory positive airway pressure, and the determining system determines, for the second volume of fluid supplied to the patient, a second volume of fluid received by the patient. An averaging system determines, based on the first and the second volumes of fluid received by the patient, a first average volume of fluid received by the patient. A comparing system compares the first average volume to a predetermined target volume, and an adjusting system adjusts the first inspiratory positive airway pressure to a second inspiratory positive airway pressure based on the comparison of the first average volume to the predetermined target volume.

[0017] These and other objects, features and characteristics of the present invention, as well as the methods of operation and functions of the related elements of structure and the combination of parts and economies of manufacture, will become more apparent upon consideration of the following description and the appended claims with reference to the accompanying drawings, all of which form a part of this specification, wherein like reference numerals designate corresponding parts in the various figures. It is to be expressly understood, however, that the drawings are for the purpose of illustration and description only and are not intended as a definition of the limits of the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

[0018] FIG. 1 is a schematic diagram of a ventilator connected to a patient via a circuit and an interface;

[0019] FIG. 2A is a time-based graph of fluid flow supplied to the patient {dot over (V)}est, fluid flow leaked from the system, typically into the atmosphere {dot over (V)}leak, and fluid flow received by the patient {dot over (V)}tot in response to operation of the ventilator shown in FIG. 1 during a single breath cycle;

[0020] FIG. 2B is a time-based graph of fluid pressure at the interface shown in FIG. 1 in response to operation of the ventilator;

[0021] FIG. 3 is a flow chart of the operation of the ventilator in accordance with a first embodiment of the present invention; and

[0022] FIG. 4 is a flow chart of the operation of the ventilator in according with a second embodiment of the present invention.

DETAILED DESCRIPTION OF THE PRESENTLY PREFERRED EMBODIMENTS OF THE INVENTION

[0023] FIG. 1 illustrates an exemplary embodiment of a pressure support system or ventilator 2 according to the principles of the present invention. As used herein, the term “ventilator” refers to any device that delivers a flow of breathing gas to a patient at a variable pressure, and is not intended to be limited to a life support ventilating system. An example of a pressure support system that provides a variable pressure to the patient based on patient's respiratory cycle that is not necessarily used for life support purposes is the pressure support system taught in U.S. Pat. Nos. 5,148,802 and 5,433,193, both to Sanders et al., the contents of which are incorporated by reference into the present application.

[0024] Ventilator 2 includes a source of pressurized fluid 4 and a pressure regulator 6 connected to receive pressurized fluid from source of pressurized fluid 4. Pressure regulator 6 regulates the pressure of the pressurized fluid supplied to a patient circuit 8, which conveys the pressure regulated fluid to a patient 10 via a patient interface device 12. A sensor 14 detects a parameter associated with the fluid flow in patient circuit 8 or in interface device 12 that can be used to determine a volume of fluid supplied to the patient from pressure regulator 6 and provides to a controller 16 a signal indicative this parameter.

[0025] In an exemplary embodiment of the present invention, sensor 14 is a flow sensor that detects the flow of fluid in patient circuit 8. This flow can be used to determine the volume of fluid provided to the patient. It is to be understood, however, that the present invention contemplates using other parameters, such as the power or current provided to a blower, to determine the flow and, hence, the volume of fluid provided to a patient. A pressure sensor 18 detects the pressure of the pressurized fluid in patient circuit 8 and, more particularly, at patient interface 12 and supplies to controller 16 a signal indicative of the detected pressure. While the point at which the flow is measured by flow sensor 14 and the pressure is measured by pressure sensor 18 are illustrated as being within ventilator 2, it is to be understood that the location at which the actual flow and pressure measurements are taken be anywhere along patient circuit 8 or patient interface 12 so long as the purpose of measuring the pressure at the patient and the volume of fluid delivered to the patient can be determined.

[0026] The present invention also contemplates providing one or more patient monitors 19 to detect other physiological conditions of the patient. Such physiological conditions can be used to monitor the patient and/or control the operation of ventilator

[0027] For example, one embodiment of the present invention contemplates that patient monitor 19 is a diaphragm electromyographic (“EMG”) detection system that detects the EMG signals produced by the diaphragm during breathing. Another example of a suitable patient monitor is an effort detector, which detects the movement of the patient's chest during respiration. Patient monitor 19 is connected to controller 16, which monitors the diaphragm EMG or effort signal supplied thereto from patient monitor 19, for example, and, in one embodiment, causes ventilator 2 to supply fluid to patient 10 during an inspiratory phase of a respiratory cycle and to terminate or reduce the supply of fluid to patient 10 during an expiratory phase. More specifically, in this embodiment of the present invention, controller 16 signals pressure regulator 6 to supply pressurized fluid to patient 10 during an inspiratory phase and to withhold or reduce the supply of pressurized fluid to patient 10 during an expiratory. Alternatively, as shown by dashed line 25 between controller 16 and pressurized fluid source 4, controller 16 can control pressurized fluid source 4 directly to supply pressurized fluid to patient 10 during inhalation and to withhold or reduce the supply of pressurized fluid from patient 10 during exhalation, thereby effectively incorporating the function of pressure regulator 6 into pressurized fluid source 4.

[0028] While the use of the diaphragm EMG or effort signal has been described above as the mechanism for triggering the ventilator, it is to be understood that the present invention contemplates using any conventional ventilator triggering technique suitable for use with a spontaneously breathing patient. For example, the pressure and/or flow generated by the patient in patient interface 12 and/or patient circuit 8 can be used to trigger the ventilator. In addition, ventilator 2, and, more specifically, controller 16, can include a timed backup so that if the patient stops breathing for a period of time exceeding a predetermined threshold, the ventilator automatically initiates a breathing cycle.

[0029] Pressurized fluid source 4 is, for example, a source of compressed gas, e.g., air, oxygen, helium-oxygen, or other oxygen mixture. The present invention also contemplates that pressurized fluid source is a piston, a bellows or a blower that receives a supply of gas, either from ambient atmosphere or a source of compressed gas, and generates a flow of such gas. Pressure regulator 6 is, for example, a poppet, solenoid, butterfly, rotary, sleeve, or any other valve or valve assembly suitable for use in controlling a flow and/or pressure of fluid delivered to a patient. As noted above controller 16 can control the pressure and/or flow of fluid from pressurized fluid source 4 directly, i.e., without the need for a dedicated pressure control valve, by controlling the speed of the piston, bellows, or blower, thereby effectively combining the functions of pressurized fluid source 4 and pressure regulator 6 as a single unit, as generally indicated by dashed line 27. For present purposes, the combined function of the source of pressurized fluid 4 and a pressure regulator 6 is referred to as a “pressure generating system.” Thus, the pressure generating system includes pressurized fluid source 4 alone, if the flow/pressure of fluid output by the pressurized fluid source can be controlled directly, for example by regulating blower speed, otherwise the pressure generating system includes the combination of source of pressurized fluid 4 and pressure regulator 6.

[0030] In one embodiment of the present invention, patient circuit 8 is a single tube or conduit 20 connected between pressure regulator 6 and interface 12, typically referred to as a single-limb circuit. In this embodiment, conduit 20 and/or patient interface 12 includes an exhaust assembly 22 that vents exhaled gases to atmosphere and, thus, represents a known leak in the breathing gas delivery system. An example of a passive exhaust assembly is a hole or slot formed in conduit 20 and/or interface 12 that communicates the interior of the conduit or interface with atmosphere, with no active control over the flow of gas from the system, thereby providing a flow of exhaust gas from the patient circuit and/or interface. The size of the hole is typically selected to be sufficient to purge exhaled gas from the patient circuit. It is to be understood, however, that a wide variety of exhaust devices and configurations are contemplated for use with the ventilator/pressure generating system of the present invention. For example, U.S. Pat. No. 5,685,296 to Zdrojkowski et al. discloses an exhalation device and method where the exhalation flow rate through the device remains substantially constant over a range of pressures in the patient circuit. This exhalation device, which is commonly referred to as a plateau exhalation valve or PEV, is suitable for use with the pressure support system of the present invention.

[0031] In another embodiment of the present invention, patient circuit 8 includes a second tube or conduit illustrated by dashed line 24 in FIG. 1, which is typically referred to as a two-limb circuit. Second tube or conduit 24 communicates fluid exhaled by patient 10 to ventilator 2, which includes an active exhaust assembly that monitors and/or controls the venting of exhaust fluids to atmosphere. An example of an active exhaust assembly is a valve that prevents fluid from exhausting to atmosphere when pressurized fluid is supplied to patient 10, i.e., during the inspiratory phase, and that allows gas to escape to atmosphere when the supply of pressurized fluid to patient 10 is terminated or reduced, i.e., during the expiratory phase. Typically, the active exhaust assembly controls the flow of exhaust gas to atmosphere to control the positive end exhalation pressure (“PEEP”) in the patient. Of course, the active exhaust need not be provided in the actuation housing of the ventilator, as generally shown in FIG. 1, but, regardless of its actual location, is typically controlled by or based on signals provided by the ventilator.

[0032] The present invention contemplates that patient interface device 12 is any device, either invasive or non-invasive, suitable for communicating a flow of breathing gas from the patient circuit to an airway of the patient. Examples of suitable patient interface devices include a nasal mask, nasal/oral mask, full-face mask, tracheal tube, endotracheal tube, and nasal pillow.

[0033] As described in detail below, the present invention contemplates adjusting the IPAP level, which is referred to as IPAPset, from one inspiratory phase to the next so that the average volume over multiple breaths corresponds to a target average volume. It is believed that by varying the IPAP level for the delivery of breathing gas to the patient so as to achieve an average volume over multiple breaths, rather than a target volume for each breath as done in the VTV or VAPS mode, for example, the ventilation mode of the present invention is more comfortable for the spontaneously breathing patient while still being responsive to the patient's changing respiratory demands.

[0034] The present invention also contemplates adjusting the pressure support level. As understood by those skilled in the art, the term “pressure support” is defined as the difference between the inspiratory positive airway pressure and the expiratory positive airway pressure. Stated mathematically, pressure support (PS) is defined as follows: PS=PAP−EPAP. Thus, adjusting the pressure support is accomplished by adjusting the IPAP or the EPAP level.

[0035] Determining the average volume over multiple breath cycles requires determining the volume of breathing gas VT delivered during each breath. This is accomplished relatively easily in a two-limb patient circuit because the ventilator controls the amount of fluid exhausted to atmosphere. In addition, there is considered to be substantially no leak from the patient circuit in a two-limb configuration. Therefore, the total volume of breathing gas delivered to the patient during each breath VT is determined using any conventional technique, such by providing a flow meter in the exhaust limb to measure the flow rate of exhaust gas and, from this, determine the volume of gas exhausted during each breath cycle, which corresponds to VT.

[0036] In a single limb circuit, however, determining the volume of breathing gas actually delivered to or received by the patient during each breath VT is more difficult due to the fact that there is a relatively large intentional leak in the patient circuit and potential unintentional leaks at the interface between the patient and the interface device. U.S. Pat. Nos. 5,148,802 to Sanders et al., 5,313,937 to Zdrojkowski et al., 5,433,193 to Sanders et al., 5,632,269 to Zdrojkowski et al., and 5,803,065 to Zdrojkowski et al., the contents of each of which are incorporated by reference into the present invention, describe techniques for detecting and estimating leak and managing the delivery of breathing gas to the patient in the presence of leaks. Although one can refer to one or more of these patents to determine how to estimate leak rate in a single-limb circuit for the purpose of determining the total flow to the patient during a breathing cycle, a brief description of this process is provided below for the sake of completeness.

[0037] In a single limb circuit, the volume of fluid VT received by patient 10 over a breath cycle is determined from a difference between the volume of fluid supplied to the patient by the ventilator, i.e., the volume of fluid output by the ventilator, and the volume of fluid leaking from the ventilator system, which includes leak from the patient circuit and leak from the patient interface device, during that breath cycle. Typically, most of the leak is from the exhaust vent in the patient circuit . More specifically, fluid leaking to atmosphere is generally the result of a known leak, such as the exhaust flow provided by exhaust assembly 22 in the single-limb circuit, and unknown leaks, such as a leak at the interface between the patient and patient interface device 12. The flow of fluid received by patient 10 at any given time is estimated using Equation 1:

{dot over (V)} est ={dot over (V)} tot −{dot over (V)} leak ,  (1)

[0038] where:

[0039] {dot over (V)}est=estimated flow of fluid received by patient 10;

[0040] {dot over (V)}tot=flow of fluid supplied to patient 10 by the pressure support device at that time; and

[0041] {dot over (V)}leak=estimated flow of fluid leaking into the atmosphere at that time.

[0042] As used herein, the “{dot over (V)}” notation refers the derivative of volume with respect to time, which is commonly referred to as “flow”.

[0043] While Equation 1 defines the estimated flow to the patient at any instant during a breath cycle, a similar relationship exists for estimating the total volume of fluid Vest delivered to the patient during a breath cycle and is defined as follows:

V est =V tot −V leak ,  (2)

[0044] where:

[0045] Vest=estimated volume of fluid received by patient 10 during the breathing cycle and corresponds to VT;

[0046] Vtot=volume of fluid supplied to patient 10 by the pressure support device during the breathing cycle; and

[0047] Vleak=estimated volume of fluid leaking into the atmosphere over the breathing cycle.

[0048] According to one leak estimation technique, {dot over (V)}leak in Equation 1 is determined as a function of the conductance between interface 12 and patient 10. For simplicity of determining {dot over (V)}leak in Equation 1, conductance Gleak between interface 12 and patient 10 is assumed to be a constant for each breath cycle and is determined using the following Equation 3: 1$\begin{array}{cc}{G}_{leak}=\frac{{\int }_0^{T_{\mathrm{breath}}}{\stackrel{.}{V}}_{\mathrm{tot}}\left(t\right)dt}{{\int }_0^{T_{\mathrm{breath}}}\sqrt{P_{\mathrm{interface}}\left(t\right)}dt},& \left(3\right)\end{array}$

[0049] where:

[0050] Gleak=conductance between interface 12 and patient 10 during the inspiratory phase;

[0051] Pinterface=fluid pressure determined at or near interface 12, which is a value measured using pressure sensor 18, for example; and

[0052] {dot over (V)}tot=flow of fluid supplied to patient 10, which is also a value measured using flow sensor 14, for example.

[0053] Conductance Gleak determined using Equation 2 is utilized in the following Equation 4 to estimate the flow of fluid leaking into the atmosphere, i.e., {dot over (V)}leak, at any given time:

{dot over (V)} leak =G leak {square root}{square root over (Pinterface)}.   (4)

[0054] During a breathing cycle, controller 2 monitors the flow of fluid supplied to patient 10 (Vtot) via flow sensor 14 and the fluid pressure determined at or near interface 12 (Pinterface) via pressure sensor 18. Using this information gathered over a complete breathing cycle, controller determines the value for 2${\int }_0^{T_{\mathrm{breath}}}{\stackrel{.}{V}}_{\mathrm{tot}}\left(t\right)dt$

[0055] and 3${\int }_0^{T_{\mathrm{breath}}}\sqrt{P_{\mathrm{interface}}\left(t\right)}dt,$

[0056] which are the terms in the numerator and denominator, respectively, for Equation 3. In an exemplary embodiment of the present invention, controller 16 samples the signals generated by flow sensor 14 and pressure sensor 18 a plurality of times, for example, 100 samples per breath cycle, to obtain {dot over (V)}tot and Pinterface during that breath cycle. Once the values for 4${\int }_0^{T_{\mathrm{breath}}}{\stackrel{.}{V}}_{\mathrm{tot}}\left(t\right)dt$

[0057] and 5${\int }_0^{T_{\mathrm{breath}}}\sqrt{P_{\mathrm{interface}}\left(t\right)}dt$

[0058] are obtained, Equation 3 can be solved so that the conductance (Gleak) associated with a particular breathing cycle is known.

[0059] To determine a value for {dot over (V)}leak at any given instant in a breath cycle, controller 16 solves Equation 4 utilizing the known value of conductance Gleak, and the fluid pressure in interface 12 at that instant, which is preferably measured using pressure sensor 18. It is to be understood that the present invention contemplate using an average value of conductance Gleak, rather than the conductance determined in the immediately preceding breath cycle. For example, the conductance for each of the last n breath(s) can be calculated and the average conductance over the n breath(s) can be used in Equation 4 to determine leak, where n is an integer. The present invention also contemplates that numerator, the denominator, or both in Equation 3 can be determined from an average of these values determined during the last n breaths.

[0060] Another technique for determine conductance Gleak at breath cycle n+1 involves solving the following equations 5-7: 6$\begin{array}{cc}{N}_{n+1}=\frac{N_n}{2}+{\int }_0^{T_{\mathrm{breath}}}\left({\stackrel{.}{V}}_{\mathrm{tot}}-{\stackrel{.}{V}}_{\mathrm{known}\mathrm{leak}}\right),& \left(5\right)\\ D_{n+1}=\frac{D_n}{2}+{\int }_0^{T_{\mathrm{breath}}}\sqrt{P_{\mathrm{interface}}},& \left(6\right)\\ G_{leakn+1}=\frac{N_{n+1}}{D_{n+1}},& \left(7\right)\end{array}$

[0061] where {dot over (V)}known leak is a predetermined known leak from the patient circuit, typically through the exhaust, port for a given pressure in the patient circuit, which is measured by pressure sensor 18, for example.

[0062] In an exemplary embodiment of the present invention, controller 16 determines {dot over (V)}leak by sampling the fluid pressure Pinterface multiple times, such as 100 times, during the breathing cycle. For each sampled pressure, controller 16 calculates {dot over (V)}leak using Equation 4, with the known value of conductance Gleak used in Equation 4 being obtained using any of the above-described techniques. By sampling the pressure multiple time during the breath cycle and determining {dot over (V)}leak at each sample, controller 16 closely approximates the total leak volume Vleak during the entire breath cycle. Knowing the total leak volume Vleak for the current breath cycle and the total volume Vtot of fluid supplied to patient 10 by the pressure support device during the current breathing cycle, which is readily determined from the measured flow, controller 16 solves Equation 2 to determine a value for the total volume Vest of fluid delivered to the patient during the current breath cycle.

[0063] For example, as shown in FIGS. 2A-2B, at time t0, during a first breath cycle 30, controller 16 samples the signal from flow sensor 14 and samples the signal from pressure sensor 18 to obtain instantaneous values of fluid flow {dot over (V)}tot (FIG. 2A) and fluid pressure Pinterface (FIG. 2B). At time t1 during first breath cycle 30, controller 16 again samples the signals from flow sensor 14 and pressure sensor 18 to obtain instantaneous values of fluid flow {dot over (V)}tot and fluid pressure Pinterface. Sampling the signals generated by flow sensor 14 and pressure sensor 18 a plurality of times during first breath cycle 30 enables controller 16 to determine a value for 7${\int }_0^{T_{\mathrm{breath}}}{\stackrel{.}{V}}_{\mathrm{tot}}\left(t\right)dt$

[0064] and a value for 8${\int }_0^{T_{\mathrm{breath}}}\sqrt{P_{\mathrm{interface}}\left(t\right)}dt$

[0065] for first breath cycle 30. Utilizing the thus obtained values for first breath cycle 30, controller 16 solves Equation 3 to obtain a value for conductance Gleak for first breath cycle 30.

[0066] During a second breath cycle 32, controller 16 obtains a plurality of samples of the signals from flow sensor 14 and pressure sensor 18. Controller 16 stores this information for second breath cycle 32 and utilizes the plural samples of the signals from flow sensor 14 and pressure sensor 18 to determine values for {dot over (V)}tot and 9${\int }_0^{T_{\mathrm{breath}}}\sqrt{P_{\mathrm{interface}}\left(t\right)}dt$

[0067] for second breath cycle 32. Controller 16 uses the thus determined values to solve Equation 3 to obtain a value for conductance Gleak for second breath cycle 32.

[0068] Next, controller 16 utilizes conductance Gleak determined for first breath cycle 30 and the samples pressures Pinterface determined for second breath cycle 32 to solve Equation 4 for each sampled pressure to obtain a value for {dot over (V)}leak for second breath cycle 32. Using the values for {dot over (V)}tot and {dot over (V)}leak determined at multiple samples through the second breath cycle 32, controller 16 determines the total volume of fluid delivered by the pressure support device Vtot and total volume Vleak or fluid that leaked from the patient circuit during the second breath cycle. Controller 16 then solves Equation 2 to determine the estimated volume of fluid Vest received by the patient during second breath cycle 32. In a similar manner, controller 16 determines for a third breath cycle (not shown) values for {dot over (V)}tot, 10${\int }_0^{T_{\mathrm{breath}}}{\stackrel{.}{V}}_{\mathrm{tot}}\left(t\right)dt,{\int }_0^{T_{\mathrm{breath}}}\sqrt{P_{\mathrm{interface}}\left(t\right)}dt,$

[0069] Gleak, and Vleak. Using the value of conductance Gleak determined for second breath cycle 32 and the pressure samples taken during the third breath cycle, controller 16 solves Equation 4 to obtain values for {dot over (V)}leak during each sample taken during the third breath cycle. Using the values of {dot over (V)}tot and {dot over (V)}leak determined for the multiple samples in the third breath cycle, controller 16 determines the total volume of fluid delivered by the pressure support device Vtot and total volume Vleak or fluid that leaked from the patient circuit during the third breath cycle. Controller 16 then solves Equation 2 to determine the estimated volume of fluid Vest for the third breath cycle. In a similar manner, controller 16 determines values for Vest for subsequent breath cycles.

[0070] As noted above, preferably controller 16 solves Equation 4 to obtain a value for {dot over (V)}leak for each sample in a breath cycle as a function of conductance Gleak determined from the immediately preceding breath cycle and Pinterface determined at each sample. Conductance Gleak used in Equation 4, however, as noted above, can be an average conductance (“AVG Gleak”) determined from a plurality of preceding breath cycles. Moreover, controller 16 can determine a value for the total leak during a breath cycle {dot over (V)}leak from conductance Gleak and the values of Pinterface taken during that same breath cycle.

[0071] For a detailed description of leak detection and management of patient flow in the presence of leaks, see the above identified patents of Sanders et al. and Zdrojkowski et al., and, in particular, U.S. Pat. No. 5,803,065 to Zdrojkowski et al., the contents of which were incorporated herein by reference above.

[0072] Controller 16 can also determine for each breath cycle a value for {dot over (V)}est in Equation 1 using regression analysis.

[0073] As shown in FIG. 2B, when pressurized fluid is supplied to patient 10 during first breath cycle 30, pressure regulator 6 sets the inspiratory positive airway pressure (“IPAP”) level for the fluid delivered to patient 10, which is identified as IPAPset in FIG. 2B and is preferably between a maximum IPAP, IPAPmax, and a minimum IPAP, IPAPmin. IPAPmax and IPAPmin are typically set by the clinician. However, the present invention also contemplates that IPAPmax, IPAPmin or both can be automatically set by the ventilator. For example, once the user sets IPAPmin, the ventilator can set IPAPmax automatically as a fixed percentage of fixed pressure above IPAPmin. IPAPmin can be set in a similar fashion after the clinician set IPAPmax.

[0074] Using the above techniques, the system of the present invention determines the volume of fluid VT delivered to a patient during a breath cycle. As noted above, if the system is a single-limb circuit, i.e., a circuit with a leak, the volume of fluid VT delivered to a patient during a breath cycle is estimated as Vest.

[0075] With reference to FIG. 3, and referring back to FIG. 1, the method for adjusting a volume of fluid supplied to a patient VT from one inspiratory phase to the next in a manner that is comfortable for the patient and responsive to the patient's changing respiratory demands will now be described. According to the principles of the present invention, adjusting a volume of fluid supplied to a patient VT is accomplished by controller 16 causing pressure regulator 6 to adjust IPAPset in accordance with the steps set forth in the flow chart shown in FIG. 3.

[0076] In response to activating ventilator 2 in step 40, controller 16 causes pressurized fluid to be supplied to patient 10 during the inspiratory phase and causes the flow of pressurized fluid to be reduced or withheld from patient 10 during exhalation. In step 42, controller 16 determines N values of VT, where N is at least one (1) or more and preferably five (5). Each value of VT is determined in the above-described manner and corresponds to the estimated volume Vest of fluid received by patient 10 during a corresponding breath cycle if the patient circuit is a single limb circuit.

[0077] In step 44, controller 16 determines a current value of VT and in step 46, controller 16 determines an average value of VT (“AVG VT”) for N+1 breath cycles. In step 48, controller 16 compares an absolute value of the difference between AVG VT and a predetermined target volume of fluid Vtarget to be received by patient 10 to a predetermined offset value Voffset. If this absolute value is less than the predetermined offset value Voffset, controller 16 branches to step 50 where the current value of IPAPset is maintained. The predetermined target value of fluid Vtarget is determined clinically for each patient 10 and the predetermined offset value Voffset can be a set value or a programmable value established by ventilator 2.

[0078] If the absolute value of the difference between AVG VT and Vtarget is greater than or equal to Voffset, controller 16 branches to step 52. In step 52, controller 16 determines if AVG VT is greater than Vtarget. If so, controller 16 branches to step 54. In step 54, controller 16 causes pressure regulator 6 to decrease IPAPset by a predetermined pressure ΔP, e.g., 0.1 cm H2O. If, however, in step 52 controller 16 determines that AVG VT is less than Vtarget, controller 16 branches to step 56. In step 56, controller 16 causes pressure regulator 6 to increase IPAPset by the predetermined pressure ΔP. Increasing or decreasing IPAPset increases or decreases, respectively, the volume of fluid VT delivered to patient 10 during the inspiratory phase.

[0079] To avoid undesirably high or low values of IPAPset, in step 58, controller 16 compares the current IPAPset to IPAPmax and IPAPmin. If the current IPAPset is greater than IPAPmax, in step 58, controller 16 causes pressure regulator 6 to clamp the current value of IPAPset to IPAPmax. Similarly, if the current value of IPAPset is less than IPAPmin, in step 58, controller 16 causes pressure regulator 6 to clamp the current value of IPAPset to IPAPmin. After completing step 58, controller 16 repeats steps 44-58 for each subsequent breath cycle.

[0080] It can thus be appreciated that step 46 determines AVG VT for the current breath cycle and N prior breath cycles. Hence, step 46 determines a moving average of AVG VT, which is utilized in steps 48 and 52. Alternatively, steps 42 and 46 can be eliminated and the current value of VT can be utilized in place of AVG VT in steps 48 and 50.

[0081] In a two-limb circuit, with the patient coupled to an invasive patient interface device, such as a trachea tube or an endotracheal tube, there is considered to be substantially no leak. Thus, VT=Vtot, which is measured directly by flow sensor 14 in FIG. 1, for use in the routine shown in FIG. 3. Therefore, in this embodiment, the determination of VT is simplified and need not be calculated using the analysis discussed above.

[0082] In the illustrated embodiment as noted above, the volume delivered to the patient is averaged over two or more, and preferably 6, breaths to determine (step 46 in FIG. 3) whether to maintain (steps 48 and 50), decrease (step 52 and 54), or increase (steps 52 and 56) IPAP by an incremental amount. However, the present invention also contemplates using the patient's minute ventilation, which is a parameter that is widely understood and generally familiar to those in the health care industry, instead of the volume averaged over a number of breaths, AVG VT, to determine whether to modify IPAP. Thus, the present invention contemplates altering steps 46-52 in FIG. 3 so that the minute ventilation (“MV”) replaces AVG VT.

[0083] A further embodiment of the process for controlling the volume of fluid delivered to a patient according to the principles of the present invention is discussed below with reference to FIG. 4. In response to activating ventilator 2 in step 60, controller 16 causes pressurized fluid to be supplied to patient 10 during the inspiratory phase and causes the flow of pressurized fluid to be reduced or withheld from patient 10 during exhalation. As noted above, a target volume VTarget is set, which is a desired volume of fluid to be delivered to the patient during each respiratory cycle.

[0084] In step 62, controller 16 monitors the patient breaths to calculate the following measures:

[0085] 1) Per Breath Tidal Volume, calculated as the average of inhaled and exhaled tidal volume,

[0086] 2) Average Breath Rate, which in a preferred embodiment is a six breath average of the breath rate expressed in breaths per minute, and

[0087] 3) Statistical Measures: such as Mean, Standard Deviation and Standard Mean. In a preferred exemplary embodiment of the present invention, the statistical measures are calculated using the per breath tidal volume data over the last 2 minutes. Of course, the present invention contemplate using other time periods over which this data is collected so long as the time period is long enough to provide meaningful data, but not so long as to make the system too slow to respond to changes in the patient. Standard Mean is the ratio of Standard Deviation over the Mean value. The purpose of the Standard Mean is discussed below with reference to step 66.

[0088] It should be noted that the present invention contemplates determining the exhaled tidal volume in an invasive or a non-invasive ventilatory system using the methods discussed above with respect to determining the inhaled tidal volume. That is, the same principles discussed above with respect to determining the inhaled tidal volume apply to determining the exhaled tidal volume. Of course, any conventional technique can be used to determine the expiratory tidal volume.

[0089] In step 64, the controllers determines whether the tidal volume each breath or respiratory cycle of the patient is within normal parameters. If so, the system proceeds to step 66 and uses the data associated with that breath in the further processing steps. If the breath data is not within normal parameters, the data associated with that breath is thrown away, is indicated by the flow chart of FIG. 4, as a return to step 62. The present invention also contemplates monitoring the number of breaths that are discarded or considered not normal, so that an alarm can be indicated, for example, if too many non-normal breaths are detected. Such an occurrence may indicate that the patient is experiencing a pronounced period of respiratory disorder, that the pressure support system is not functioning properly, or both.

[0090] A further embodiment of the present invention contemplates accepting breath data under certain circumstances even if the breath data is not within normal parameters. This is done so that “bad” data is not completely ignored, but can be used to indicate a trend in the change of the condition of the patient. For example, the present invention contemplates that if five non-normal breaths are detected out of the last ten breaths, the data from one of the non-normal breaths is provided to the rest of the processing routine, i.e., it is provided to step 66 for use in determining AVG VT. The non-normal breath data to be provided to step 66 in this circumstance can be the data associated with the 5th non-normal breath detected, an average of the data associated with the five non-normal breaths, or any variation thereof, so long as some of the non-normal information is provided to step 66. The purpose of this is to allow relatively large changes in the condition of the patient, such as the patient rolling over, moving the mask on their face, increase flow resistance due to a cold, to be taken into consideration by the processing routine of the present invention, at least on a relatively slow basis, rather than ignoring or discarding such non-normal data it in its entirety.

[0091] Determining whether respiratory cycle is within normal parameters involves a two part test, in which each part must be satisfied in order to allow the current breath to be used in the further processing discussed below, i.e., not discarded. The first part is a normal distribution test, where the per breath tidal volume of the current breath is compared to the Mean value determined in step 62. For example, the present invention discards the current breath data if the current per breath tidal volume is greater than or equal to +/−2 standard deviations of the Mean determined in step 62. Of course, the present invention contemplates using other values for the standard deviation in deciding whether to accept or reject data, and is not intended to be limited to the use or two standard deviations.

[0092] The second part of the two-part test look for symmetry in the volume exhaled and inhaled. If the inhaled tidal volume and exhaled tidal volume are within 50% of each other, then the current breath is considered a normal breath. This test eliminates breaths that contain mismatched tidal volume resulting from transitory leak conditions, mouths openings, sighs, and/or mis-triggers of the ventilator. Again, the present invention contemplates using other values for the percentage considered acceptable in this step.

[0093] In step 66, breaths that pass the normalcy test of step 64 are used in determining the pressure support, or change in pressure support, to be provided to the patient. As understood by those skilled in the art, the term “pressure support” is defined as the difference between the inspiratory positive airway pressure (IPAP) and the expiratory positive airway pressure (EPAP). Stated mathematically, pressure support (PS) is defined as follows: PS=IPAP−EPAP.

[0094] The average tidal volume (AVG VT) is calculated in step 66 using the normal breaths determined in step 64, with VT being determined using the technique discussed above with respect to step 62. In a presently preferred embodiment, the average tidal volume is calculated over the last 1 and 2 minutes. Then, an average error volume (AVG VE) is determined as the difference between the target volume (Vtarget), i.e., the volume control value, and the 1 minute average tidal volume AVG VT.

[0095] In step 66, controller 16 also calculates an average pressure support, which is the pressure provided to the patient over the last 2 minutes. In addition, an estimated elastance Eest is determined as the ratio of pressure support average (2 minutes) over the average tidal volume (two minutes). It can be appreciated that time periods other than the two minute time frame can be used to determine the estimated elastance, so long as the time frame of the average tidal volume and the time frame of the average pressure support are the same.

[0096] True elastance is typically measured when muscle effort is zero. The present inventors recognize that during spontaneous breaths, this estimate includes muscle effort, but may be used for relative assessment of the relationship between pressure support and tidal volume. The present invention uses this approximation to determine how much pressure support must changed to produce the resultant tidal volume.

[0097] In step 66, the controller also determines the patient's stability, meaning whether or not the patient's breathing, i.e., tidal volume, has been stable over a certain period of time. To determine the patient's stability, the standard mean determined in step 62 is evaluated over a certain period of time, which, in a presently preferred embodiment, is over the last two minutes. Changes in leak, periodic breathing, REM sleep are all marked by a high measure of standard mean. In an exemplary embodiment of the present invention, a standard mean greater than 20% is considered a high degree of variability, and a standard means less than 20% is considered relatively stable.

[0098] As discussed below with reference to step 70, the present invention uses different rates of change for the pressure support depending on whether the patient is stable or unstable in their breathing. If the patient is relatively stable in their breathing, the changes made to the pressure support are faster than if the patient is unstable. As a result, pressure changes will be made more slowly, when necessary, for patients that have a less stable breathing pattern.

[0099] In step 68, the controller determines pressure support error (PSE) as the result of multiplying the average error volume AVG VE by the estimated elastance Eest.

[0100] Pressure support error PSE represents an estimate of how much pressure support must be added or removed from the current pressure support level of the patient and is updated on a per breath basis.

[0101] Stated mathematically, the determination of the pressure support error can summarized as follows: 11$\begin{array}{cc}PSE=E_{est}\times AVG{V}_{Error}=\frac{\sum _{2\mathrm{minutes}}PS}{\sum _{2\mathrm{minutes}}{V}_T}\times \sum _{1\mathrm{minute}}{V}_E=\frac{\sum _{2\mathrm{minutes}}PS}{\sum _{2\mathrm{minutes}}{V}_T}\times \left(\frac{\sum _{1\mathrm{minute}}{V}_T}{n}-V_{\mathrm{target}}\right),& \left(8\right)\end{array}$

[0102] wherein n is the number of volumes in the 1 minute period, so that 12$\frac{\sum _{1\mathrm{minute}}{V}_T}{n}$

[0103] corresponds to the average tidal volume for the 1 minute period (AVG VT).

[0104] To control the patient tidal volume, the pressure support level is changed gradually over several minutes in step 70 so as to move the pressure support error toward zero. In presently preferred embodiment, the EPAP pressure remains fixed, and the IPAP pressure is ramped over several minutes. The ramp time is limited by the use of a one minute averaging array. The array must be filled with new data before the decision to increase or decrease the pressure can be made again so prevent controlling the system faster than the measurement system operates.

[0105] As noted above, the rate of IPAP pressure change, i.e., the slope of the IPAP ramp, is determined by the patient stability determined in step 66. If the patient is stable the pressure can be changed quickly, e.g., 1 minute per cmH2O, otherwise the IPAP pressure moves move slowly, e.g., 2 minutes per cmH2O.

[0106] Based on the foregoing, it can be appreciated that the present invention provides an apparatus and method for adjusting the volume of fluid supplied to a patient during a breathing cycle as a function of the volume of fluid received by the patient during a previous breathing cycle, thereby avoiding patient discomfort. This allows the patient to alter his or her breathing pattern temporality, such as by taking a very shallow or a very deep breath, during one breathing cycle without the ventilator overreacting to these minor variation.

[0107] The invention has been described with reference to the preferred embodiments. Obvious modifications and alterations will occur to others upon reading and understanding the preceding detailed description. It is intended that the invention be construed as including all such modifications and alterations insofar as they come within the scope of the appended claims or the equivalents thereof.

Claims

1. A method of adjusting a volume of a breathing gas supplied to a patient, the method comprising the steps of: (a) supplying a flow of breathing gas to a patient over a plurality of respiratory cycles of such a patient; (b) determining, for each respiratory cycle, a tidal volume of the flow of breathing gas received by such a patient; (c) determining an average tidal volume of the flow of breathing gas received by such a patient from the volumes of breathing gas received by such a patient during the plurality of respiratory cycles; (d) determining an average error volume by comparing the average tidal volume to a predetermined target volume; and (e) adjusting a pressure of the flow of breathing gas based on the average error volume.

2. The method as set forth in claim 1, wherein step (b) includes calculating the tidal volume of the flow of breathing gas received by such a patient as an average of an inhaled tidal volume and an exhaled tidal volume for the respiratory cycle.

3. The method as set forth in claim 1, further comprising: determining, for each respiratory cycle, whether the tidal volume of the flow of breathing gas received by the patient is within normal parameters; discarding the tidal volume for a respiratory cycle that is not within normal parameters; and using the tidal volume for a respiratory cycle in step (c) if the tidal volume is within normal parameters.

4. The method as set forth in claim 3, wherein determining, for each respiratory cycle, whether the tidal volume of the flow of breathing gas received by the patient is within normal parameters comprises comparing the tidal volume of the current respiratory cycle with a normal distribution of tidal volumes determined over a plurality of breaths.

5. The method as set forth in claim 3, wherein determining, for each respiratory cycle, whether the tidal volume of breathing gas received by the patient is within normal parameters comprises comparing, for the current respiratory cycle, an inhaled tidal volume with an exhaled tidal volume.

6. The method as set forth in claim 3, wherein determining, for each respiratory cycle, whether the tidal volume of breathing gas received by the patient is within normal parameters comprises: comparing the tidal volume of the current respiratory cycle with a normal distribution of tidal volumes determined over a plurality of breaths; and comparing, for the current respiratory cycle, an inhaled tidal volume with an exhaled tidal volume.

7. The method as set forth in claim 1, further comprising determining an estimated elastance for the patient and wherein the step of adjusting the pressure of the flow of breathing gas is also done based on the estimated elastance and the average error volume.

8. The method as set forth in claim 7, wherein determining the estimated elastance comprises: determining an average pressure support provided to such a patient over a period of time; determining an average of the tidal volumes received by such a patient over the period of time; and determining the estimated elastance as the ratio of the average pressure support over the average of the tidal volumes for the period of time.

9. The method as set forth in claim 7, wherein adjusting the pressure of the flow of breathing gas includes: determining a pressure support error as a product of the estimated elastance and the average error volume; and adjusting the pressure of the flow of breathing gas to minimize the pressure support error.

10. The method as set forth in claim 1, further comprising determining whether recent tidal volumes of such a patient have been stable, and wherein a rate of change by which the pressure of the flow of breathing gas is adjusted in step (e) is based on the result of the determination of whether the recent tidal volumes have been stable.

11. The method as set forth in claim 10, wherein determining whether recent tidal volumes of such a patient have been stable comprises: determining a standard mean for the recent tidal volumes as a ratio of a standard deviation over a mean value of the recent tidal volumes; and comparing the standard mean to a predetermined threshold.

12. The method as set forth in claim 1, wherein adjusting the pressure of the flow of breathing gas comprises adjusting at least a portion of an inspiratory positive airway pressure, at least a portion of an expiratory positive airway pressure, or both.

13. An apparatus for supplying breathing gas to a patient, the apparatus comprising: a pressure generating system adapted to provide a flow of breathing gas to a patient; a patient circuit operatively coupled to the pressure generating system to deliver the flow of breathing gas to such a patient; an interface device operatively coupled to the patient circuit to communicate the flow of breathing gas to an airway of such a patient; at least one sensor operatively coupled to one of the pressure generating system, the patient circuit, and the interface device to detect a parameter indicative of a volume of breathing gas delivered to such a patient; and a controller operatively coupled to the sensor and the pressure generating system, wherein the controller: (a) determines, for each respiratory cycle, a tidal volume of breathing gas received by such a patient based on the parameter indicative of the volume of breathing gas delivered to such a patient provided by the sensor; (b) determines an average tidal volume of breathing gas received by such a patient from the volumes of breathing gas received by such a patient during the plurality of respiratory cycles; (c) determines an average error volume by comparing the average tidal volume to a predetermined target volume; and (d) causes the pressure generating system to adjust a pressure of the flow of breathing gas based on the average error volume.

14. The apparatus as set forth in claim 13, wherein the controller calculates the tidal volume of breathing gas received by such a patient as an average of an inhaled tidal volume and an exhaled tidal volume for the respiratory cycle.

15. The apparatus as set forth in claim 13, wherein the controller: determines, for each respiratory cycle, whether the tidal volume of breathing gas received by the patient is within normal parameters; discards the tidal volume for a respiratory cycle that is not within normal parameters; and uses the tidal volume for a respiratory cycle in determining an average error volume if the tidal volume is within normal parameters.

16. The apparatus as set forth in claim 15, wherein the controller determines, for each respiratory cycle, whether the tidal volume of breathing gas received by the patient is within normal parameters by comparing the tidal volume of the current respiratory cycle with a normal distribution of tidal volumes determined over a plurality of breaths.

17. The apparatus as set forth in claim 15, wherein the controller determines, for each respiratory cycle, whether the tidal volume of breathing gas received by the patient is within normal parameters by comparing, for the current respiratory cycle, an inhaled tidal volume with an exhaled tidal volume.

18. The apparatus as set forth in claim 15, wherein the controller determines, for each respiratory cycle, whether the tidal volume of breathing gas received by the patient is within normal parameters by: comparing the tidal volume of the current respiratory cycle with a normal distribution of tidal volumes determined over a plurality of breaths; and comparing, for the current respiratory cycle, an inhaled tidal volume with an exhaled tidal volume.

19. The apparatus as set forth in claim 13, wherein the controller determines an estimated elastance for the patient and adjusts the pressure of the flow of breathing gas, via the pressure generating system, based on the estimated elastance and the average error volume.

20. The apparatus as set forth in claim 19, wherein the controller determines the estimated elastance by: determining an average pressure support provided to such a patient over a period of time; determining an average of the tidal volumes received by such a patient over the period of time; and determining the estimated elastance as the ratio of the average pressure support and the average of the tidal volumes over the period of time.

21. The apparatus as set forth in claim 19, wherein the controller determines causes the pressure generating system to adjust the pressure of the flow of breathing gas by: determining a pressure support error as a product of the estimated elastance and the average error volume; and causing the pressure generating system to adjust the pressure of the flow of breathing gas so as to minimize the pressure support error.

22. The apparatus as set forth in claim 13, wherein the controller determines whether recent tidal volumes of such a patient have been stable, and controls an amount by which the pressure of the flow of breathing gas is adjusted by the pressure generating system based on the result of the determination of whether the recent tidal volumes have been stable.

23. The apparatus as set forth in claim 22, wherein the controller determines whether recent tidal volumes of such a patient have been stable by: determining a standard mean for the recent tidal volumes as a ratio of a standard deviation over a mean value of the recent tidal volumes; and comparing the standard mean to a predetermined threshold.

24. The apparatus as set forth in claim 13, wherein the controller adjusts the pressure of the flow of breathing gas via the pressure generating system by adjusting at least a portion of an inspiratory positive airway pressure, at least a portion of an expiratory positive airway pressure, or both.