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    16 Abstract A system including a breathing apparatus and a processor is configured to raise a first positive end-expiratory pressure PEEP level to at least a second PEEP level above said first PEEP level andsubsequently lowering said second PEEP level to said first PEEP level and to calculate a lungmechanics equation relating total lung volume above functional residual capacity (FRC) totranspulmonary pressure (PTP) of a lung connected to said breathing apparatus, based on a change in end-expiratory lung volume (DEELV) between said first PEEP level and said second PEEP level.
    公开号:SE1550671A1
    申请号:SE1550671
    申请日:2015-05-25
    公开日:2016-11-26
    发明作者:Stenqvist Ola；LUNDIN Stefan
    申请人:The Lung Barometry Sweden AB；
    IPC主号:
    专利说明:

    Method System and Software for Protective Ventilation Field of the lnvention: This invention pertains in general to the field of breathing apparatuses. The invention relates moreparticularly to methods and systems for ventilating a patient and for preventing damage to the lungsof a patient being ventilated, as well as to clinical decisions systems preferably including user interfaces of such breathing apparatuses, in particular graphical user interfaces (GUl's) thereof.
    Background of the lnvention: During the polio epidemic in Copenhagen in 1952, manually controlled ventilation was used toprovide adequate gas exchange in patients to normalize oxygen levels, remove carbon dioxide, andthereby save the lives of patients with compromised respiration. Just one year later during a polioepidemic in Stockholm, ventilator treatment was introduced on a large scale to treat not only poliopatients but to provide respiratory treatment to patients with respiration compromised by othercauses. The focus of mechanical ventilation on normalizing gas exchange lead to the use of largetidal volumes, often over 10-12 ml/kg body weight, along with concomitant high airway pressures. ln1967, increased positive end-expiratory airway pressure (PEEP) was introduced as a method toimprove gas exchange. Successively, it was realized that there were side-effects of mechanicalventilation, such as compromising effects on circulation and injury to lung parenchyma by the highpressures and tidal volumes used (barotrauma and volutrauma). Additionally, injury to the lung parenchyma can cause secondary failure in other organs.
    A breathing apparatus may be set to provide desired gas exchange in the lungs by adjusting PEEP andtidal volume (VT). Some combinations of PEEP and VT may result in an end inspiratorytranspulmonary pressure (PTPH) that is high enough to cause damage to the lungs. During PEEPtreatment, the therapist seeks a reasonable compromise between the risk of lung tissue damage anddesired or acceptable gas exchange. An improperly selected ventilator strategy can cause injury tothe lung tissue, or Ventilator lnduced Lung lnjury (VILI). The selection of a PEEP level that providesdesired gas exchange without risking damage to the lungs is difficult in many cases and a number ofapproaches for selecting safe and effective PEEP levels have been used with limited clinical success.Most methods for selecting a PEEP level for respiratory therapy are based on the oxygenation of thepatient using PEEP/FIOZ (fraction of inspired oxygen) tables or are applied without knowing whetherthe individual patient is a responder or non-responder to PEEP. Some methods to set PEEP are based on measurement of total respiratory system mechanics, i.e. the combined chest wall and lung mechanics (e.g. total elastance), rather than measuring lung mechanics (e.g. lung elastance)separately. A limitation of existing breathing apparatus and associated ventilation strategies is thatthey do not provide a way for the user to avoid a strategy that may cause V|L| or to ensure that astrategy will not result in an end inspiratory transpulmonary pressure (PTPH) that is below a pre-determined maximum value. Another drawback of existing systems and methods for ventilation is that, PTP is measured using esophageal pressure as a surrogate for pleural pressure.
    WO 2011/157855 A1, which is incorporated by reference in its entirety for all purposes, especiallyequations 1-17 and their descriptions on pages 7-14, discloses that it is possible to calculate anestimated transpulmonary pressure after measuring lung elastance as the ratio of change in end-expiratory airway pressure (APEEP) to change in end-expiratory lung volume (AEELV), APEEP/AEELVfollowing a PEEP step maneuver. WO 2011/157855 does not disclose systems comprising graphic visualizations based upon calculated values of lung elastance.
    During ventilation of a patient clinicians often seek to maintain a certain ventilation strategy for atreatment which is believed particularly advantageous for a ventilated patient. WO 2014/124684 A1,which is incorporated by reference, in particular Figs. 3-9 and their corresponding descriptions,discloses a breathing apparatus with a ventilation strategy tool comprising a graphic visualization toolthat provides a combination of a target indication one or more ventilation related parameters of aventilation strategy and a reciprocating animation of parameter(s) relative the target indication,which may be based upon user input. WO 2014/124684 does not disclose calculating values for lungelastance or using such values for avoiding V|L|.
    There is hitherto no flexible tool to provide clinicians with a status of an on-going ventilation in aclear and easily understandable way when it comes to the crucial point of how the current patientventilation is related to a chosen ventilation strategy. lt would be particularly desirable for such atool to be adaptable to the status an on-going ventilation of a patient during the ventilation itself.Also, it would be desired if the tool provided a feedback to the clinician that can be understood froma distance from a breathing apparatus. lt would be desired, for instance, to provide a quick overviewof a current ventilation strategy to the clinical user. Each ventilation strategy has a target. A quickidentification of compliance of an ongoing ventilation with this target to the clinical user would bedesired and allow for faster clinical decision taking related to the ventilation strategy. For instance, apatient in an isolation room or during an x-ray examination might not be approached by the clinicianwith undue burden. Thus, such a tool would be advantageous if it provided the clinician with acurrent status of a ventilation in relation to a desired strategy, even for a projected outcome of adjustments to clinical ventilation parameters, e.g. in a simulated ventilation.
    For instance for education of clinicians, it would be advantageous if this tool was provideable withouta patient connected to the breathing apparatus, e.g. in a simulated ventilation, e.g. based on a testlung connected to the breathing apparatus. Hence, there is a need for such a tool implemented in asystem including a breathing apparatus that can provide the ventilation, and based on adjustmentsthereof pursues the desired ventilation strategy. Clinical decisions related to the treatment of aventilated patient might then be facilitated. Based on a target input from a clinical user, thebreathing apparatus may automatically adjust remaining ventilation parameters for safe and reliableventilation ensuring sufficient oxygenation of a connected patient. A corresponding method,software and system are provided. Treatment of the ventilated patient may thus be improved. Costof care can potentially reduced by the more effective treatment that can be provided related to the chosen ventilation strategy.
    Thus, an improved breathing system for providing a clinical tool providing clear and easilyunderstandable status for an on-going ventilation strategy in relation to a desired outcome thereofwould be advantageous. This need and the above-mentioned limitations of the current state of theart are addressed by the current disclosure, wherein the present invention provides an improvement over the state of the art in the field of breathing apparatus and ventilation.
    Brief Summary of the lnvention ln one aspect, the invention is a system comprising a breathing apparatus, a display unit and aprocessing unit operatively connected to the display unit and configured to provide a graphicalvisualization on the display unit including information on transpulmonary pressure and lung volume,such as a pressure vs. volume curve, for a patient connected to the breathing apparatus. Thegraphical visualization may alternatively or additionally include an indication of tidal volume (VT),positive end-expiratory pressure (PEEP), end-inspiratory transpulmonary pressure (PTPE. or PTPEI),end-expiratory lung volume (EELV), and/or end-inspiratory lung volume (EILV). The graphicalvisualization may alternatively or additionally include breath-by-breath change in EELV. ln oneembodiment, the graphical display comprises a total lung volume vs. pressure graph in which PEEP = PTPEE. ln another aspect, the invention is a decision support system comprising a breathing apparatus, adisplay unit and a processing unit operatively connected to the display unit, wherein the processingunit is configured to provide on the display unit a graphical visualization including a combination of VT, PEEP, and PTPEI. The graphical visualization may alternatively or additionally include an indication of EELV, EILV, and/or breath-by-breath change in EELV. Decision support may be automated preventand/or alert an operator to the setting of operational parameters of the breathing apparatus that arecalculated to result in a PTPEI above a pre-determined value, for example to prevent VILI.Additionally or alternatively, the decision support system may provide a graphic visualization thatdraws the attention of an operator to one or more parameter settings that are calculated to result ina PTPEI above a pre-determined value, for example to prevent VILI. Decision support may comprise agraphic representation of a ventilation strategy, for example in the form of PEEP and VT settings to be entered by a user. ln yet another aspect, the invention is a computer-readable medium comprising a computer programfor processing by a processing unit for providing the graphical visualizations of one or both of the first two aspects of the invention.
    The invention is based upon an estimation, or calculation, of lung elastance rather than an estimationof the total elastance, in which lung elastance and chest wall elastance are combined. The selectionof pressures and volumes delivered by the ventilator are thereby strictly adapted to the condition ofthe lung as opposed to a combination of lung and chest wall mechanics. ln one aspect, the inventionprovides a method for obtaining a complete lung volume / lung pressure curve or lung pressure curve/lung volume (V/PTP or PTP/V curve) from end-expiration at functional residual capacity to end-inspiration of the highest PEEP level of a PEEP trial and to identify lower and upper inflection points.This method, which provides estimated values for Lung Elastance (EL) can be performed in less than 5minutes, making it possible to provide a breath-by-breath PTP versus time curve in the form of avisual display that is easily interpretable by an operator of a ventilator. The combination of thecomplete lung PTP/V curve and the tidal PTP/V ([PTP/VT]) curve can be used to adjust both tidalvolume and PEEP level to minimize the risk of lung tissue damage in the individual patient. A lung orlungs may be used to refer to the lung or lungs of a human or non-human patient or to a test lung, model lung, or artificial lung.
    Brief Description of the DrawingsFig. 1A and B are examples of V/P graphs that may be used to estimate of AEELV between ZEEP/FRCand baseline clinical PEEP; Figs. ZA-C are graphs of breath by breath change in EELV after a PEEP change plotted on a logarithmicscale;Fig. 3 is an example of a graph showing breath by breath airway, esophageal and transpulmonary pressure volume curves during a PEEP trial from ZEEP to 16 cmHzO; Figs. 4A and B are graphical displays of airway pressure and EELV measurements breath-by-breathAEELV, measurments; Figs. 4C and D are graphic displays of breath-by-breath changes in EELV for low inlflection and highinflection zones; Figs. 5A and B are examples graphs of complete estimated lung P/V curves corresponding topulmonary ARDS and extrapulmonary ARDS, respectively; Fig. 6A is graph of the complete PTP/V curve in a pulmonary ARDS patient; Fig. 6B is the same graph as Fig. 6A including system suggested PEEP and tidal volume settings thatresult in an end-inspiratory PTP that is below a predetermined maximum level; Fig. 7A is graph of a complete PTP/V curve in an extrapulmonary ARDS patient; and Fig. 7B is the same graph as 7A including system suggested PEEP and tidal volume that result in an end-inspiratory PTP that is below a predetermined maximum level.
    Detailed Description of the lnvention The invention is based, in part, on the discovery that it is possible to obtain a PTP vs. volume curve(P/V curve) for a patient in a way that allows a breathing apparatus system and/or a user of such asystem to quickly determine whether or not a selected combination of positive end-expiratorypressure (PEEP) and tidal volume (VT) will result in an end-inspiratory transpulmonary pressure (PTPE.or PTPEI) that is above a pre-determined limit, e.g. to prevent damage to the lungs. The inventorshave discovered how to obtain a complete lung P/V curve using 1 or more PEEP steps. Furthermore, breath-by-breath Determination of end-expiratory lung volume changes, AEELV An incremental PEEP trial results in a "PEEP induced" inflation of the lungs. The increase in EELVfollowing a PEEP increase can be calculated as the difference in EELV between two PEEP levels,where the EELV at each PEEP level is determined by a dilution method or by EIT (electric impedancetomography) or any method for determination of the absolute lung volume. However, a directmeasurement of AEELV as by the ventilator pneumotachograph/spirometer is preferred for a rapid and accurate determination of AEELV.
    Lung elastance (EL)and transpulmonary pressure (PTP) determinationThe conventional method for determining EL and PTP is by using esophageal pressure measurementsas a surrogate for pleural pressure, where PTP is the difference in tidal airway pressure and tidal esophageal pressure. Measurement of esophageal pressure is time consuming and there is no consensus on the interpretation of the absolute values or values in relation to atmospheric pressure.As a consequence, only tidal variations in esophageal pressure are used. Also, the measurement oftidal esophageal pressure poses several obstacles. Measurements are sensitive to the filling of theballoon of the measurement catheter and position of the catheter. Several other factors have adetrimental effect on measurement results and all together precision is low. Thus, esophagealpressure measurements can be used for calculation of a lung P/V curve in the individual patient during a PEEP trial as described below, but they are not preferred.
    Total respiratory system elastance (EToT) is the difference in end-inspiratory airway plateau pressureand the end-expiratory airway pressure (APAW) divided by the tidal volume (VT), APAW/ VT.
    Chest wall elastance (ECW) is the difference in end-inspiratory esophageal plateau pressure and theend-expiratory esophageal pressure (APES) divided by the tidal volume (VT), APES/ VT. Lungelastance (EL) is the difference between total respiratory system elastance and chest wall elastance,ETOT- ECW. Tidal transpulmonary pressure variation (APTP) is calculated as EL x VT. APTP of a tidal volume equal to the change in end-expiratory lung volume (VT=AEELV) is calculated as EL x AEELV.
    Determination of the complete lung P/V curve from zero end-expiratory airway pressure(ZEEP) and at functional residual capacity (FRC), ZEEP/FRC to end-inspiration of a highestPEEP level By esophageal pressure measurements: The PTP at FRC and ZEEP is set to zero, representing the PTP of the most dependent region of theaerated lung in supine/semi-recumbent position. A prerequisite for the determination of the lungP/V curve by esophageal pressure measurement is that a PEEP trial is performed and the stepwiseAEELV and EL determined at each PEEP step.
    At end-inspiration at ZEEP and a lung volume of VTOPEEPO: PTPEIPEEPO =ELPEEP0 x VTPEEPO.
    At end-expiration of the first PEEP level after PEEPO, EEpEEpl and a lung volume of AEELVM: PTPEEPEEN= ELPEEPO x AEELVM.
    At end-inspiration at PEEP1 and a lung volume of AEELVO-l + VTI FEM: PTPElpEEpl = PTPEEPEEN + ELpEEpl xvTPEm.
    At end-expiration of PEEP2 and a lung volume of AEELVM + AEELVH: PTPEEPEEPZ = PTPEEpEEpl + ELpEEpl xAEELVH.
    At end-inspiration of PEEP2 and a lung volume of AEELV0_1+ AEELVH + VTZ: PTPEIPEEPZ = PTPEEPEEPZ +ELPEEPZ x VTPEEPZ.
    At end-expiration of PEEP3 and a lung volume of AEELVM + AEELVH + AEELVH = AEELVOQ, PTPEEPEEPQ, = PTPEEPEEPZ + ELpEEpz X AEELVZQ,At end-inspiration of PEEP3 and a lung volume of AEELVM + AEELVH + AEELVH + VT3: PTPElpEEpg = PTPEEPEEP3 + ELPEEP3 X VTPEEP3- By Lung Barometry The basic Lung Barometry concept is that lung elastance, EL, is equal to the change in PEEP divided bythe corresponding change in end-expiratory lung volume, APEEP/AEELV. Thus, the determination ofAEELV is an inherent part of the method. Airway pressure measurements are very precise andmodern ventilators keep set PEEP levels constant. The AEELV following a PEEP change can bedetermined by the cumulative difference between inspiratory and expiratory tidal volumes. TheseAEELV measurements have a high precision (e.g. Fig. 4B). The determination of EL by Lung Barometryonly demands a change in PEEP and a spirometric determination of the resulting AEELV. This is a verysimple and precise method, which is much more suitable than esophageal measurement-based for determination of the lung P/V curve during a PEEP trial.
    Total respiratory system elastance (ETOT) is the difference in end-inspiratory airway plateau pressureand the end-expiratory airway pressure (APAW) divided by the tidal volume (VT), APAW/ VT.
    Chest wall elastance (ECW) is the difference between total respiratory system elastance and lungelastance, ETOT- EL, where ETOT is determined using a tidal volume equal to AEELV. Lung elastance(EL) is the ratio of change in end-expiratory airway pressure (APEEP) to the corresponding change inend-expiratory lung volume (AEELV), APEEP/AEELV. APTP of a tidal volume equal to the change inend-expiratory lung volume (VT=AEELV) is by definition equal to the change in end-expiratory airway pressure (APEEP).
    The basic measurement algorithm - Example Start from a steady state clinical PEEP level.
    Increase PEEP by 70% of the APAW. The PEEP increase is preferably around 70% but may be greateror less than 70%, for example 30%, 40%, 50%, 60%, 80%, 90%, or 100%.
    Determine the increase in EELV (AEELVup) as the cumulative difference between inspiratory andexpiratory tidal volumes during = 1 minute, e.g. 30, 40, 45, 50, 55, 60, 65, 70, or 75 seconds. Returnto baseline PEEP = 2 minutes after the increase in PEEP, for example 90, 100, 110, 120, 130, 140, or150 seconds.
    Determine the decrease in EELV (AEELVdown) as the cumulative difference between inspiratory andexpiratory tidal volumes during = 1 minute.
    Calculate the mean AEELV as (AEELVup + AEELVdown)/2.
    Set the tidal volume to mean AEELV.
    Determine total respiratory system elastance ETOT as APAW/VT=meanAEELv.
    Calculate lung elastance (EL) as APEEP/AEELVmean.
    Calculate chest wall elastance (ECW) as the difference between total respiratory system elastanceand lung elastance, ECW = ETOT- EL.
    Calculate the ratio EL/ETOT and calculate the ratio of EL to ETOT at the higher PEEP level as (ETOTHP - EcwBQ/ETOTHP.
    Example - Determining PTP using basic Lung Barometry The end-expiratory PTP at baseline (PTPEEBL), clinical PEEP and baseline lung volume of zero is equalto the end-expiratory airway pressure (PEEP): PTPEEBL = PAWEEBL.
    The end-expiratory PTP at the higher PEEP level (PTPEEHP) and a lung volume above baseline equal toAEELVmean is equal to the PEEP at the higher PEEP level: PTPEEHP = PAWEEHP.
    The end-inspiratory PTP at baseline PEEP and a lung volume above baseline EELV equal to VTBLisPTPEIBL = PTPEEBL + APAWVTBL - ECWBL x VTBL.
    The end-inspiratory PTP at the higher PEEP level and a lung volume above baseline equal toAEELVmean + VTHP is PTPEIHP = PTPEEHP + APAWVTHP- ECWBLx VTHP.
    ECW remains mainly constant when changing PEEP.
    Example - Estimation of AEELV between ZEEP/FRC and baseline EELV Data of PTP at end-expiration and end-inspiration at baseline and the higher PEEP level is plottedversus corresponding EELV data. The best fit polynomial curve of the second and the third degreecurve are plotted. The equation for the best fit curves are solved for zero PTP, which gives the meanvolumes where the curves intersect with the volume axis at zero PTP. This estimated volume,AEELVO-BL, is added to all the previous EELV values, which means that EELVBL is equal to AEELVO-BLand that end-inspiratory lung volume at baseline lung volume is AEELVO-BL + VTBL. EELV at the highPEEP level is AEELVO-BL + AEELVBL-HP and the end-inspiratory lung volume at the high PEEP level isAEELVO-BL + AEELVBL-HP + VTHP.
    The first expiration PTP As ECW remains constant when PEEP is changed, the PTP of the first expiration after changing PEEPcan be determined as APEEP - ECW x First expiration volume increase. Using this additional PTP/Vpoint increases precision when estimating the AEELV between ZEEP/FRC and baseline PEEP. Also the PTP of subsequent expirations until a new steady state can be estimated in the same way.
    The extended Lung Barometric measurement algorithm - Example The extended algorithm contains two consecutive PEEP steps, HP1 and HP2, still starting from abaseline clinical PEEP, but now reaching a higher lung volume and PTP.
    The first increased PEEP level (PEEPHP1) is maintained only for a minute and AEELVBL-HP1up isdetermined as described for the basic algorithm.
    The size of the second PEEP step is predicted as the difference in end-inspiratory plateau airwaypressure between the high and the baseline PEEP levels, PAWEIHP1-PAWEEBL. AEELVHP1-HP2up is determined as described for the basic algorithm.
    The second increased PEEP level (PEEPHP2) is maintained for a minute before returning PEEP to HP1.
    AEELVHP1-HP2 down and mean AEELVHP1-HP2up-down are determined as described for the basicalgorithm.
    EL between PEEPHP1 and PEEPHP2 is determined as the difference in PEEP between HP2 and HP1divided by the mean change in EELV between HP2 and HP1, APEEPHPl-HP2/AEELVHP1-HP2.
    ETOT at HP2 is calculated as APAWHPZ/VTHPZ.
    ECW at HP2 is calculated as ETOTHP2-ELHP2.
    A minute after lowering PEEP from HP2 to HP1, PEEP is lowered to baseline PEEP level. During thefirst minute after decreasing PEEP, AEELVBL-HP1down and meanAEELVBL-HP1 are determined asdescribed for the basic algorithm.
    The tidal volume is set to mean AEELVBL-HP1.
    ETOT is determined as APAWBL/VLmEanAEELVBL-HP1.
    EL is calculated as APEEP/AEELVmeanBL-HPL ECW is calculated using ECWBL = ETOTBL - ELBL.
    The ratio of EL to ETOT at baseline is calculated: ELBL/ETOTBL.
    The ratio of EL to ETOT at PEEPHP1 is calculated: ELHPI/ETOTBP1.
    The ratio of EL to ETOT at the PEEPHP2 is calculated: (ETOTHP2- ECWHP1)/ETOTHP2.
    Example - Transpulmonary pressure by extended Lung Barometry ECW is assumed to remain essentially constant when changing PEEP.
    The end-expiratory PTP at baseline (PTPEEBL), clinical PEEP and baseline lung volume of zero is equalto the end-expiratory airway pressure (PEEP); PTPEEBL = PAWEEBL.
    The end-expiratory PTP at the higher PEEP level (PTPEEHP1) and a lung volume above baseline equal to AEELVmeanBL-HP1 is equal to the PEEP at PEEPHP1;PTPEEHP1 = PAWEEHP1.
    The end-expiratory PTP at the highest PEEP level (PTPEEHP2) and a lung volume above baseline equalto AEELVmeanBL-HP1 + AEELVmeanHP1-HP2 is equal to the PEEP at PEEPHPZ: PTPEEHP2 = PAWEEHP2 The end-inspiratory PTP at baseline PEEP and a lung volume above baseline EELV equal to VTBL is PTPEIBL = PTPEEBL + APAWVTBL - ECWBL x VTBL The end-inspiratory PTP at PEEPHPI and a lung volume above baseline equal to AEELVmean + VTHP isPTPElHPl = PTPEEHPl + APAWVTHPI - ECWHPl x VTHP1 The end-inspiratory PTP at PEEPHP1 and a lung volume above baseline equal to AEELVmean + VTHP is PTPEIHPZ = PTPEEHPZ + APAWVTHPZ - ECWH P2 X VTHP2 Example - Estimation of AEELV between ZEEP/FRC and baseline EELV by extended Lung BarometryFig. 1 shows how EELV between a baseline PEEP and ZEEP/FRC can be determined without loweringPEEP to zero. Data of PTP at end-expiration and end-inspiration at baseline and PEEPHP1 andPEEPHP2 are plotted versus corresponding EELV data. A best fit polynomial of the second and thirddegree curve is plotted. The equations for the best fit curves are solved for zero PTP, which gives themean volume where the curve intersects with the volume axis at zero PTP. This estimated volume,AEELVO-BL, is added to all the previous EELV values, which means that EELVBL is equal to AEELVO-BLand that end-inspiratory lung volume at baseline lung volume is AEELVO-BL + VTBL. EELV at PEEPHP1is AEELVO-BL + AEELVBL-HP and the end-inspiratory lung volume at the high PEEP level is AEELVO-BL +AEELVBL-HP1 + VTHP1. The end-expiratory lung volume at PEEPH P2, EELVH P2 is AEELVO-BL + AEELVBL-HP1 + AEELVHP1-HP2 and the end-inspiratory lung volume at the high PEEP level is AEELVO-BL +AEELVBL-HPZ + VTHP2. Fig. 1A and B are graphs showing estimations of AEELV between ZEEP andbaseline clinical PEEP. Fig. 1A shows a polynomial second degree best fit curve equation for thePTP/V points of the PEEP trial. Fig. 1B shows a polynomial third degree best fit curve equation for thePTP/V points of the PEEP trial. The mean of the values for the intercepts of the curves and the y-axis are used. For Fig. 1A and B the mean of the values is (301+180)/2 = 240 ml.
    Example - Identification of inflection points/zones The establishment of a new P/V equilibrium after increasing PEEP involves multiple breaths, wherethe lung volume increase decreases breath-by-breath until a new steady state is established. lf thevolume increase (AEELV) of each breath is plotted on a logarithmic volume scale, an upwards convex(increasing lung elastance) or concave (decreasing lung elastance) or linear slope of lung elastancecan be identified for the lung volume between the two PEEP levels. Figs. 2A-C are examples of logEELV vs. breath graphs that correspond to decreasing, increasing, and constant EL between two different PEEP levels.
    Identification of non-linearity at a volume range between the end-inspiratory lung volume (EILV) of two PEEP levels 11 Using the breath by breath end-inspiratory plateau airway pressure (PAWEI), an increasing EL isreflected in an increasing PAWEI after the first breath after PEEP is increased. lf the PAWEI decreases,EL decreases. lf PAWEI is constant, EL is constant at the highest volume levels. Fig. 3 shows anexample of a type of graph that can be used to identify non-linearity in a volume range between theEILV at two PEEP levels. Breath by breath airway, esophageal and transpulmonary pressure volumecurves during a PEEP trial from ZEEP to 16 cmH2O are shown. The progress of the PAWEI is circled.During PEEP change from 4 to 8 cmH2O, PAWEI decreases breath by breath, indicating a decreasingEL. During PEEP change from 8 to 12 cmH2O PAWEI remains mainly constant, indicating anunchanging EL. During PEEP change from 12 to 16 cmH2O PAWEI increases breath by breath, indicating an increasing EL (overdistension).
    Example - Lung Barometric measurement display When a measurement procedure is intended to start, a measurement display appears on the screen.Baseline airway pressures and tidal volumes are presented and steady state is determined. WhenPEEP is increased, the breath by breath increase in EELV is shown on a logarithmic scale to identifynon-linearity, i.e. increase or decrease in EL between two PEEP levels (e.g. Figs. 2A-C). Additionally,the cumulative increase in EELV may displayed breath by breath and the AEELVup result is displayed(Fig. 4C). Figs. 4A and B show an illustrative example of such a display in which EL is 70 ml/cmH20,APTP/APAW at PEEP=5 cmH2O is 0.77, APTP/APAW at PEEP=15 cmH2O is 0.65, APEEPup andAPEEPdown are each 10 cmH20, AEELVup is 680 ml, and AEELVdown is 720 ml.
    The PAWEI may additionally be displayed breath by breath on an enlarged scale to identify increasingor decreasing EL at the end-inspiratory lung-volume level. PEEP is lowered and, after about 2minutes, the AEELVdown and the mean of AEELVup and AEELVdown is shown and EL(APEEP/AEELVmean) may be displayed. The ratio of APTP/APAW for baseline PEEP level and for the higher PEEP level may be displayed.
    Examples - Decision support and monitoring display The complete lung VL/PTP (or PTP/VL) curve with estimated ZEEP/FRC may be displayed, in whichPTPEE is equal to PEEP. Figs. 5A and B are examples graphs of complete estimated lung P/V curvescorresponding to pulmonary acute respiratory distress syndrome (ARDS) and extrapulmonary ARDS,respectively. These curves may be generated from a single PEEP increase-decrease cycle or morepreferably an extended PEEP cycle in which PEEP is increased in two steps followed by PEEP decrease in two steps. Using an equation for the best fit of the lung P/V curve, decision support is possible. 12 Example - Pulmonary ARDS The following example corresponds to complete estimated lung P/V curves shown in Figs. 6A and Bfor pulmonary ARDS. Using the equation for the best fit lung P/V curve (y=0.0x3+0.8x2+34), and thefact that the end-expiratory PTP changes as much as PEEP (PAWEE) is changed, this display providesinformation that makes decision support readily available. ln this case of pulmonary ARDS, aninjurious end-inspiratory PTP level of 27 at PEEP 12 can be identified. The corresponding end-expiratory and end-inspiratory lung volume levels (above FRC) are 525 and 1125 ml. lf oxygenation isinadequate, a suggested increase in PEEP level to 15 cmHzO with an increase in EELV from 525 to 690ml, to improve oxygenation can be combined with a reduction of tidal volume from 600 to 350 ml,resulting in an end-inspiratory lung volume to 1040 ml and a lowered end-inspiratory PTP to 24 cmHzO, slightly below the upper inflection point.
    Example - Extrapulmonary ARDS The following example corresponds to complete estimated lung P/V curves shown in Figs. 7A and Bfor pulmonary ARDS. Using the equation for the best fit lung P/V curve (y=-0.0x3+2.5x2+36) and thefact that the end-expiratory PTP changes as much as PEEP (PAWEE) is changed, this display providesinformation that makes decision support readily available. ln this case of extrapulmonary ARDS, thePTPEI level of 18 cmHzO at PEEP 12 can be identified. The corresponding end-expiratory and end-inspiratory lung volume levels (above FRC) are 400 and 975 ml. lf oxygenation is inadequate, asuggested increase of PEEP level to 16 cmHzO with an increase in EELV from 400 to 775 ml can becombined with a reduction of tidal volume from 575 to 425 ml, resulting in an end-inspiratory lungvolume to 1200 ml and an end-inspiratory PTP only 1.5 cmHzO higher than before, i.e. 19.5 cmHzOand, well below a possible risk level (pre-determined maximum PTP) of 24 cmHZO. The pre-determined maximum PTP may be higher or lower than 24 cmHZO as determined by a user (e.g. a clinician or respiratory therapist).
    Example - measurement sequence and complete lung P/V calculation procedureIncrease PEEP from baseline clinical value and determine the increase in EELV, AEELVup.Decrease PEEP to baseline level and determine the decrease in EELV, AEELVdown.Calculate the mean AEELVup and down, AEELVmean.
    Set tidal volume equal to AEELVmean.
    Determine respiratory system elastance, EToT as PAWE|p|ateau/VT=AEELVmean.
    Determine lung elastance, EL, as APEEP/AEELVmean. 13 Determine chest wall elastance, ECW as EToT - EL.
    Determine PTPEI at baseline PEEP as baseline PAWHBL- ECW x VT.
    Determine PTPEI at increased PEEP as PAWEI Hpl - ECW x VT.
    Plot PEEPBL, PEEPHP1, PTPEIBL and PTPHpl versus corresponding lung volume.
    Determine the best fit curve equation (polynomial, second and/or third degree) of PTP/V points.
    Use the equation for decision support.
    The systems and methods described herein may be embodied by a computer program or a pluralityof computer programs, which may exist in a variety of forms both active and inactive in a singlecomputer system or across multiple computer systems. For example, they may exist as softwareprogram(s) comprised of program instructions in source code, object code, executable code, or otherformats for performing some of the method steps. Any of the above may be embodied on acomputer readable medium, which includes storage devices and signals in compressed oruncompressed form. The term ”computer” refers to any electronic device comprising a processor,such as a general-purpose central processing unit (CPU), a specific purpose processor, or amicrocontroller. A computer is capable of receiving data (an input), performing a sequence ofpredetermined operations on received data, and producing a result in the form of information or signals (an output) resulting from the predetermined operations.
    权利要求:
    Claims (10)
    [1] 1. A system including a breathing apparatus and a processing unit configured to: raise a first positive end-expiratory pressure PEEP level to at least a second PEEP levelabove said first PEEP level and subsequently lowering said second PEEP level to said first PEEPleveland calculate a lung mechanics equation relating total lung volume above functional residualcapacity (FRC) to transpulmonary pressure (PTP) of a lung connected to said breathingapparatus, based on a change in end-expiratory lung volume (DEELV) between said first PEEP level and said second PEEP level.
    [2] 2. The system of claim 1, wherein said processing unit is further configured to calculate any one ofend-inspiratory transpulmonary pressure (PTPH), tidal volume (VT) and PEEP from any two of the other of PTPH, VT and PEEP using said lung mechanics equation.
    [3] 3. The system of claim 1 or claim 2, and further comprising a display unit operatively connected tosaid processing unit, said processing unit being configured to provide on said display unit a graphical visualization of said lung mechanics equation.
    [4] 4. The system of claim 3, wherein said graphical visualization is a complete lung P/V curve generated using one or more step changes in PEEP level.
    [5] 5. The system of claim 3, further comprising a graphical visualization including information relating breath-by-breath changes in lung volume in response to a change in PEEP level.
    [6] 6. A method of setting a desired value of a ventilation parameter in a breathing apparatus, saidmethod comprising:calculating a value for PTPE| using said lung mechanics equation calculated by the system of claim 2 and selecting a VT and PEEP based upon said lung mechanics equation.
    [7] 7. A method of automatically adjusting at least one second ventilation parameter in a breathingapparatus for a ventilation of a connected patient based on a target input of a first ventilation parameter from a clinical user, said method including: raising a first positive end-expiratory pressure PEEP level to at least a second PEEP levelabove said first PEEP level and subsequently lowering said second PEEP level to said first PEEP level, calculating a lung mechanics equation relating total lung volume above functional residualcapacity (FRC) to transpulmonary pressure (PTP) of a lung connected to said breathing apparatus,based on a change in end-expiratory lung volume (DEELV) between said first PEEP level and saidsecond PEEP level, and adjusting at least one of PTPH, VT and PEEP based on said lung mechanics equation.
    [8] 8. The method of claim 7 and further comprising calculating breath-by-breath change in EELV inresponse to a change in PEEP level from a first PEEP level to a second PEEP level and therefromdetermining whether the lungs exhibit increased, decreased, or constant elastance between said first and second PEEP levels.
    [9] 9. A computer program, preferably embodies on a computer-readable medium, for performing the method of any of claims 6-8.
    [10] 10. A graphical user interface for a system according to any of claims 1-5, said graphical userinterface including a graphical visualization including a combination of values for PTPH, VT and PEEP,wherein at least of said of PTPH, VT and PEEP values is calculated based on said lung mechanics equation.
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    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    SE1550671A|SE538864C2|2015-05-25|2015-05-25|Method System and Software for Protective Ventilation|SE1550671A| SE538864C2|2015-05-25|2015-05-25|Method System and Software for Protective Ventilation|
    US15/574,468| US10881822B2|2015-05-25|2016-05-25|Method, system and software for protective ventilation|
    JP2017561715A| JP6783253B2|2015-05-25|2016-05-25|Methods, systems, and software for protection ventilation|
    CN201680030040.8A| CN108513540B|2015-05-25|2016-05-25|Methods, systems, and software for protective ventilation|
    PCT/EP2016/061866| WO2016189069A1|2015-05-25|2016-05-25|Method, system and software for protective ventilation|
    EP16725135.4A| EP3302663B1|2015-05-25|2016-05-25|Method, system and software for protective ventilation|
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