US20070062533A1 - Apparatus and method for identifying FRC and PEEP characteristics - Google Patents

Apparatus and method for identifying FRC and PEEP characteristics Download PDF

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Publication number
US20070062533A1
US20070062533A1 US11/438,244 US43824406A US2007062533A1 US 20070062533 A1 US20070062533 A1 US 20070062533A1 US 43824406 A US43824406 A US 43824406A US 2007062533 A1 US2007062533 A1 US 2007062533A1
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Prior art keywords
peep
patient
residual capacity
functional residual
ventilator
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US11/438,244
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English (en)
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Gary Choncholas
Ronald Tobia
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General Electric Co
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Individual
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Priority claimed from US11/358,573 external-priority patent/US20070062532A1/en
Application filed by Individual filed Critical Individual
Priority to US11/438,244 priority Critical patent/US20070062533A1/en
Assigned to THE GENERAL ELECTRIC COMPANY reassignment THE GENERAL ELECTRIC COMPANY ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: CHONCHOLAS, GARY J., TOBIA, RONALD L.
Priority to JP2006242211A priority patent/JP2007083031A/ja
Priority to EP06254844.1A priority patent/EP1767236B1/en
Publication of US20070062533A1 publication Critical patent/US20070062533A1/en
Priority to US13/240,383 priority patent/US8469027B2/en
Abandoned legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Measuring devices for evaluating the respiratory organs
    • A61B5/091—Measuring volume of inspired or expired gases, e.g. to determine lung capacity
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
    • A61M16/0051—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes with alarm devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
    • A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes operated by electrical means
    • A61M16/022—Control means therefor
    • A61M16/024—Control means therefor including calculation means, e.g. using a processor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
    • A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
    • A61M16/0816—Joints or connectors
    • A61M16/0833—T- or Y-type connectors, e.g. Y-piece
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • A61M2016/0027—Accessories therefor, e.g. sensors, vibrators, negative pressure pressure meter
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
    • A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
    • A61M2016/0036—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the breathing tube and used in both inspiratory and expiratory phase
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
    • A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
    • A61M2016/0039—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the inspiratory circuit
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
    • A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
    • A61M2016/0042—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the expiratory circuit
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2230/00—Measuring parameters of the user
    • A61M2230/40—Respiratory characteristics
    • A61M2230/43—Composition of exhalation
    • A61M2230/432—Composition of exhalation partial CO2 pressure (P-CO2)
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2230/00—Measuring parameters of the user
    • A61M2230/40—Respiratory characteristics
    • A61M2230/43—Composition of exhalation
    • A61M2230/435—Composition of exhalation partial O2 pressure (P-O2)

Definitions

  • the present invention relates to an apparatus and method for determining and displaying functional residual capacity data and other pulmonary parameters, such as positive end expiratory pressure (PEEP) data, for patients breathing with the aid of a mechanical ventilator, such as a critical care ventilator.
  • PEEP positive end expiratory pressure
  • the invention also determines and displays relationships between these and other parameters.
  • Functional residual capacity is the gas volume remaining in the lungs after unforced expiration or exhalation.
  • FRC Functional residual capacity
  • Several methods are currently used to measure functional residual capacity. In the body plethysmography technique, the patient is placed in a gas tight body box. The patient's airway is sealingly connected to a breathing conduit connected to the exterior of the body box. By measuring lung pressures and pressures in the box, at various respiratory states and breathing gas valve flow control conditions, the functional residual capacity of the patient can be determined.
  • helium dilution technique Another technique for measuring functional residual capacity is the helium dilution technique. This is a closed circuit method in which the patient inhales from a source of helium of known concentration and volume. When the concentration of helium in the source and in the lungs has reached equilibrium, the resulting helium concentration can be used to determine the functional residual capacity of the patient's lungs.
  • a further technique for determining functional residual capacity is the inert gas wash-out technique. This technique is based on a determination of the amount of gas exhaled from the patient's lungs and corresponding changes in gas concentrations in the exhaled gas.
  • the gas used for the measurement is inert in the sense that it is not consumed by metabolic activity during respiration. While a number of gases may be used for such a measurement of functional residual capacity, it is convenient to use nitrogen for this purpose.
  • the lung volume forming the functional residual capacity of the lung will contain nitrogen in the same percentage as air, i.e. approximately 80%, the remaining 20% of air being oxygen.
  • the subject commences breathing gases in which oxygen is at a different concentration than 20%.
  • the patient commences breathing pure oxygen.
  • nitrogen in the lungs is replaced by oxygen, or, stated conversely, the nitrogen is “washed out” of the lungs by the oxygen.
  • the breathing of pure oxygen could continue until all nitrogen is washed out of the lungs, in most cases, the breathing of oxygen continues until the nitrogen concentration in the exhaled breathing gases falls below a given concentration.
  • a single determination of functional residual capacity provides important information regarding the pulmonary state of the patient. However, it is often highly desirable from a diagnostic or therapeutic standpoint to have available trends or changes in the functional residual capacity of a patient over time.
  • an increase in PEEP increases functional residual capacity.
  • One component is due to stretching of the lung by the increased pressure.
  • the pressure in the lungs drops until it approaches airway pressure.
  • the alveoli or air sacs in the lungs deflate. If alveolar sacs collapse completely, more pressure is required upon inspiration to overcome the alveolar resistance and re-inflate the alveolar sacs. If this resistance cannot be overcome, the volume of such sacs are not included in the functional residual capacity of the patient's lungs.
  • An optimal PEEP is one that keeps the lung open but avoids overpressurization of the lung. It is often termed the “open lung PEEP.”
  • action such as performing a suction routine, administering a nebulized medication, or changing the ventilation parameters of the ventilator can also influence functional residual capacity and it would be helpful to be able to easily determine the effect of such actions on functional residual capacity.
  • An embodiment of the present invention comprises an apparatus and method that achieves the highly advantageous features noted above.
  • the functional residual capacity of a mechanically ventilated patient may be determined at the bedside of the patient without the need to move the patient to a laboratory.
  • By associating the apparatus with the ventilator only a single device need be employed to both ventilate the patient and determine functional residual capacity.
  • the determined functional residual capacity may be advantageously displayed in conjunction with earlier determinations and in conjunction with other pulmonary conditions, such as PEEP. Changes, or trends, in functional residual capacity over time may thus be discerned, along with changes in the other pulmonary conditions.
  • the foregoing provides an attending clinician with significant information for assessing the state of, and trends in, the functional residual capacity of the patient, as well as the relationship between the patient's residual capacity and the other factors, so that the clinician can fully discern the functional residual capacity condition of the patient.
  • the apparatus and method of the present invention determines and displays related PEEP and functional residual capacity values. This enables the clinician to note, for example, the point at which increases in PEEP produce little, if any, further increases in functional residual capacity.
  • the apparatus and method of the present invention also determines and displays a showing of the amount of lung volume recruited or de-recruited as the PEEP is changed. This allows the clinician to distinguish between changes in functional residual capacity due to lung stretching or contracting and those arising from recruitment or de-recruitment.
  • FIG. 1 is a general diagram of a mechanical ventilator and associated apparatus for ventilating a patient.
  • FIG. 2 shows an endotracheal tube with a tracheal pressure sensor suitable for use in the present invention.
  • FIG. 3 shows a ventilator display unit presenting an initial display screen for use in the present invention.
  • FIG. 4 is a chart showing the relationship among a plurality of screens employed in the present invention.
  • FIG. 5 shows a display screen for displaying functional residual capacity data and related data.
  • FIG. 6 shows a display for use in scaling the display shown in FIG. 5 .
  • FIG. 7 is a flow chart showing the steps for carrying out a measurement of functional residual capacity.
  • FIG. 8 shows a display displaying a log of events and actions that may impact the determination of functional residual capacity.
  • FIG. 9 shows a display showing the effect of changes in PEEP on functional residual capacity.
  • FIG. 9A shows a display showing changes in PEEP and functional residual capacity before and after a recruitment maneuver.
  • FIG. 9B shows a display showing the relationship of changes in PEEP to corresponding changes in functional residual capacity.
  • FIG. 10 shows a display showing spirometry data.
  • FIG. 11 shows a display for making setup adjustments for the screen shown in FIG. 10 .
  • FIGS. 12 a and 12 b show a display showing relationships among functional residual capacity, PEEP, and recruited lung volume.
  • FIG. 13 is a flow chart showing the steps for carrying out a method for obtaining the relationships shown in FIGS. 12 a and 12 b.
  • FIG. 14 is a graph showing the manner in which recruited/de-recruited volume is determined by the present invention.
  • FIG. 1 shows mechanical ventilator 10 for providing breathing gases to patient 12 .
  • Ventilator 10 receives air in conduit 14 from an appropriate source, not shown, such as a cylinder of pressurized air or a hospital air supply manifold.
  • Ventilator 10 also receives pressurized oxygen in conduit 16 also from an appropriate source, not shown, such as a cylinder or manifold.
  • the flow of air in ventilator 10 is measured by flow sensor 18 and controlled by valve 20 .
  • the flow of oxygen is measured by flow sensor 22 and controlled by valve 24 .
  • the operation of valves 20 and 24 is established by a control device such as central processing unit 26 in the ventilator.
  • the air and oxygen are mixed in conduit 28 of ventilator 10 and provided to inspiratory limb 30 of breathing circuit 32 .
  • Inspiratory limb 30 is connected to one arm of Y-connector 34 .
  • Another arm of Y-connector 34 is connected to patient limb 36 .
  • patient limb 36 provides breathing gases to lungs 38 of patient 12 .
  • Patient limb 36 receives breathing gases from the lungs of the patient during expiration.
  • Patient limb 36 may include components such as a humidifier for the breathing gases, a heater for the breathing gases, a nebulizer, or a water trap (not shown).
  • the breathing gases expired by patient 12 are provided through patient limb 36 and Y-connector 34 to expiratory limb 46 of breathing circuit 32 .
  • the expired breathing gases in expiratory limb 46 are provided through valve 54 and flow sensor 56 for discharge from ventilator 10 .
  • Valve 54 may be used to establish the PEEP for patient 12 .
  • Patient limb 36 includes gas flow and pressure sensor 57 which may be of the type shown in U.S. Pat. No. 5,088,332.
  • a pair of pressure ports and lines 58 , 60 are placed on either side of a flow restriction in the sensor and the pressure difference developed across the flow restriction is used by flow measurement unit 62 in gas module 64 to measure gas flow in patient limb 36 .
  • One of the pressure lines is connected to pressure measurement unit 66 to measure the pressure in patient limb 36 .
  • Sensor 57 also provides for a gas sampling line 68 which is connected to gas analyzer 70 .
  • Gas analyzer 70 may measure the amount of oxygen and carbon dioxide in the breathing gases. Knowing the amounts of oxygen and carbon dioxide in the breathing gases enables the amount of nitrogen to be determined as the total amount less the amounts of carbon dioxide and oxygen.
  • Respiratory and metabolic gas module 64 may comprise that made and sold by GE Healthcare as a Datex-Ohmeda MCOVX gas module.
  • the output of gas module 64 is provided in data bus 72 to central processing unit 74 in ventilator display unit 76 .
  • Central processing unit 26 in ventilator 10 is also connected to central processing unit 74 via data bus 78 .
  • endotracheal tube 90 shown in FIG. 2 may be used.
  • Endotracheal tube 90 has end 92 for connection to patient limb 36 .
  • endotracheal tube 90 extends through the mouth and into the trachea of patient 12 to provide an airway passage to lungs 38 .
  • Endotracheal tube 90 includes pressure sensor catheter 94 that extends from end 96 to provide a pressure sampling point that is close to lungs 38 of patient 12 when the endotracheal tube is inserted in the patient and can thus obtain a highly accurate indication of the pressure in the lungs.
  • An intermediate portion of catheter 94 may lie within endotracheal tube 90 .
  • the proximal portion exits the endotracheal tube and is connected via A-A to a pressure transducer and to an auxiliary input to ventilator display unit 76 .
  • the pressure obtained from catheter 94 is termed Paux. While FIGS. 1 and 2 show a connection to ventilator display unit 76 for this purpose, the connection may, alternatively, be to gas module 64 .
  • Display unit 76 of ventilator 10 receives information from the ventilator and gas module 64 and is used by the clinician to control the pneumatic control components of ventilator 10 that deliver breathing gases to patient 12 via data bus 78 . Additionally, central processing unit 74 in display unit 76 carries out the determination of functional residual capacity, recruited/de-recruited volumes, and other quantities employed in the present invention. It will be appreciated that other CPU configurations, such as a single CPU for the ventilator and its display unit may be used, if desired.
  • Ventilator display unit 76 includes user interface 100 and display 102 .
  • Display 102 is shown in greater detail in FIG. 3 .
  • Display 102 is divided into a number of display portions 102 a - g for displaying inputted, sensed, and computed information.
  • Display portions 62 a though 102 f relate primarily to the operation of ventilator 10 and the ventilation of patient 12 and are discussed briefly below.
  • Display screen portion 102 g displays information and relationships in accordance with the present invention, as described in detail below.
  • Display portion 102 a provides for the display of operating information of ventilator 10 .
  • the portion shows the type of ventilation being performed by ventilator 10 , in the exemplary case of FIG. 3 , synchronized, intermittent, mandatory ventilation, or SIMV-volume controlled ventilation.
  • Portion 102 a also provides a display of operating information inputted into ventilator 10 including the percentage of oxygen for the breathing gases, tidal volume (TV), breathing rate, inspiration time (T insp ), amount of positive end expiratory pressure (PEEP) and the pressure limit (P limit ) set for the volume controlled ventilation.
  • an appropriate one of buttons 104 a through 104 f is actuated.
  • Control knob 106 is rotated to enter a desired value for the selected option and pressed to confirm the new parameter value.
  • Further ventilator functions may be controlled by pressing a button that controls a specialized function such as ventilator setup button 72 that establishes other ventilation modes for patient 12 , spirometry button 74 for showing and controlling the display of spirometry information, 100% 0 2 button 76 , nebulizer button 78 , and procedures button 80 that controls specialized procedures for ventilator 10 .
  • Display portion 102 b of display 102 shows airway pressure data as measured from sensor 57 .
  • Portion 102 c shows textual information relating to the flow of breathing gases to the patient obtained from sensor 57
  • portion 102 d shows pressure data from catheter 94 in the endotracheal tube 90 during ventilation of patient 12 .
  • Portion 102 e of display 102 shows the information in regions 102 b , 102 c , and 102 d in graphic form and includes an indication of certain other operating information, such as the mode of ventilation SIMV-VC, and whether certain features of the present invention are operational or not.
  • Display portion 102 f of display 102 shows additional data as selected by the clinician.
  • end tidal CO 2 E t CO 2
  • lung compliance E t CO 2
  • expiratory alveolar minute volume MVe (alv)
  • respiratory rate MVe (alv)
  • total positive end expiratory pressure MVi (alv)
  • inspiratory alveolar minute volume MVi (alv)
  • Display portion 102 a - f remain generally unchanged as the present invention is practiced although, as noted above, the clinician may select the information to be shown in certain portions, such as portion 102 f.
  • Display screen 102 g is the part of display 102 employed in the present invention. As shown in FIG. 4 and in FIGS. 5, 6 , 8 and 9 - 12 , the content of this screen will change, depending on the inventive feature being utilized, the different content in screen 102 g being identified as 102 g 1 , 102 g 2 , 102 g 3 , etc. in the appropriate figures of the drawing.
  • each screen 102 g will include a menu or control portion 108 , a graphic portion 110 and tabular portion 112 .
  • graphic portion 110 contains a pair of orthogonal axes by which data can be graphically presented. The clinician may navigate and control the screen using control knob 106 .
  • Control knob 106 is rotated to scroll through the menu options displayed in menu portion 108 , depressed to select a menu option, rotated again to establish a numerical value for the selected option when appropriate, and depressed again to enter the value into ventilator display unit 76 or to confirm selection of the menu option.
  • FIG. 3 shows an initial content for screen 102 g relating to spirometry.
  • spirometry illustrates the relationship between inspired gas volumes and the pressure in the lungs as the patient breathes.
  • the graphic form of the data is normally in a loop, a portion of which is formed during inspiration and the other portion of which is formed during expiration in the manner shown in FIG. 10 .
  • the tabular portion 112 provides fields in which various obtained and computed ventilation and lung properties may be displayed.
  • Menu portion 108 allows the clinician to select a number of options with respect to the display and use of the information shown in graphic and tabular portions 110 and 112 .
  • Menu portion 108 also allows the clinician to select a further screen at 116 for adjusting the scaling for the abscissa and ordinate of graph 110 and the setup for spirometry measurements at 118 .
  • the clinician may also select screens that allow the functional residual capacity (FRC) features of the present invention and the spirometry features of the present invention to be carried out by selecting items 120 and 122 , respectively.
  • FRC functional residual capacity
  • the spirometry features of the present invention are identified by applicant as SpiroDynamics or the abbreviation SpiroD.
  • FIG. 4 shows the architecture of the screens 102 g used in the present invention.
  • the spirometry screen shown in FIG. 3 as screen 102 g 1 is the initial screen appearing as screen 102 g .
  • associated with this screen are screens for spirometry scaling and spirometry setup.
  • the clinician can select either a screen relating to functional residual capacity, namely screen 102 g 2 shown FIG. 5 or a screen relating to SpiroDynamics comprising screen 102 g 3 of FIG. 10 .
  • the screen format of FIG. 5 is termed “FRC INview.”
  • the view of FIG. 10 is termed “spiroD”.
  • the FRC INview showing of 102 g 2 includes screen shown in FIG. 6 that allows for scaling of the quantities shown graphically in FIG. 5 .
  • a further selection on the FRC INview screen allows the clinician to select the FRC log screen shown in FIG. 8 as screen 102 g 4 .
  • Selections on either of the FRC INview screen 102 g 2 or the SpiroDynamic screen 102 g 3 allows selection of a PEEP INview screen shown in FIG. 9 as 102 g 5 . As hereinafter described, this screen allows the clinician to see the relationship between functional residual capacity and PEEP to assist in selecting an appropriate PEEP for patient 12 .
  • an on/off selection option in PEEP INview screen 102 g 5 allows the clinician to display lung INview screen 102 g 6 shown in FIG. 12 .
  • the information contained in this screen relates functional residual capacity, PEEP, and recruited/de-recruited lung volumes to further assist the clinician in setting the appropriate level of PEEP.
  • the flow chart of FIG. 7 shows a method for determining and displaying functional residual capacity information for patient 12 .
  • the clinician uses a screen in the format of 102 g 2 of FIG. 5 . It is assumed that the clinician has previously established an oxygen percentage for the breathing gases to be provided by ventilator 10 using button 104 a , control knob 106 and screen region 102 a , at step 200 . In the example shown in FIG. 3 , the oxygen percentage is 50%. Ventilator 10 can be operated with the set percentage of oxygen to provide breathing gases to patient 12 at step 202 .
  • the clinician sets a different level for the oxygen content of the breathing gases. This is performed by selecting the FRC 0 2 field 206 in menu portion 68 of screen 102 g 1 and appropriately establishing the FRC 0 2 value.
  • the amount of change may be an increase or decrease from the previously set level established at step 200 ; however it must be an amount sufficient to perform the functional residual capacity analysis. A change of at least 10% is preferable in order to obtain an accurate indication of the functional residual capacity.
  • a default setting of a 10% increase over the current setting may be provided.
  • the level of oxygen set by the clinician “tracks” changes made in the oxygen content of the breathing gases at the ventilator, as for example by actuating button 104 a .
  • the ventilator oxygen is originally 50% as shown in FIG. 3
  • the FRC 02 shown in FIG. 5 is 60%
  • the FRC 02 amount will automatically move to 80%.
  • the alteration of the oxygen content of the breathing gases is carried out in step 208 of FIG. 7 .
  • an alteration in the form of an increase to 75% O 2 is shown in FIG. 5 .
  • a single functional residual capacity determination by the present method may be selected by the appropriate field 212 in menu 68 .
  • a series of FRC determinations or cycles may be selected, with a series interval, set in field 214 , between each determination.
  • the interval may be between one and twelve hours in increments of one hour.
  • the time when the next functional residual capacity determination begins is shown in field 215 .
  • functional residual capacity measurements can be set to occur automatically in conjunction with certain procedures controlled by ventilator 10 , such as immediately prior and/or after a period of nebulized drug therapy, recruitment maneuvers, a suction procedure, or a change in ventilator setting.
  • Functional residual capacity measurement may be initiated, terminated, delayed, interrupted, or prevented in accordance with the occurrence of events, such as those noted above, that may affect the accuracy of the functional residual capacity measurement.
  • a functional residual capacity measurement may be terminated for a high oxygen procedure for patient 12 and then resumed or started after a “lock out” period.
  • the initial or base line amount of nitrogen in the expired breathing gases is determined at step 216 . As noted above this may be determined by subtracting the amounts of oxygen and carbon dioxide, as determined by gas analyzer 70 , from the total amount of the breathing gases, as determined using flow sensor 62 .
  • the breathing gases for patient 12 may include the inert gas helium and amounts of helium expired by the patient could be used in a functional residual capacity measure in the manner described herein.
  • breathing gases having the increased amount of oxygen shown in data field 105 are provided to patient 12 in step 218 .
  • the increased percentage of oxygen in the breathing gases will wash a portion of the nitrogen or other inert gas out of lungs 38 of patient 12 with each breath of the patient.
  • the amount of breathing gases inspired and expired by patient 12 with each breath i.e. the tidal volume, is a lung volume that is in addition to the residual volume of the lungs found after expiration.
  • the tidal volume is also smaller than the residual volume. For a healthy adult a typical tidal volume is 400-700 ml whereas the residual volume or functional residual capacity is about 2000 ml. Therefore, only a portion of the nitrogen in the lungs 38 of patient 12 is replaced by the increased amount of oxygen with each breath.
  • the amount of nitrogen washed out of the lungs in each breath is determined by subtracting the amount of oxygen and carbon dioxide from the amount of breathing gases expired by patient 12 during each breath obtained using flow sensor 68 . See step 220 . Knowing the amount of expired breathing gases, the initial amount of expired nitrogen and the amount expired in each expiration by patient 12 , a functional residual capacity quantity can be determined for each successive breath in steps 222 a , 222 b . . . 222 n . Any inert gas wash out/wash in functional residual capacity measurement technique may be used, a suitable technique for determining functional residual capacity for use in the present invention being described in U.S. Pat. No. 6,139,506.
  • the functional residual capacity quantity as determined after each successive breath will tend to increase as nitrogen continues to be washed out of the lungs of the patient by the increased oxygen in the breathing gases.
  • functional residual capacity volume that lies behind intrinsic lung resistance does not mix as quickly with inspired gases compared to functional residual capacity volume that is pneumatically connected to the trachea through a lower resistance path.
  • the magnitude of breath-to-breath increases in functional residual capacity that are noted are an indication of the amount of intrinsic resistance within the lung gas transfer pathways.
  • additional functional residual capacity volume that is registered many breaths into the functional residual capacity measurement procedure is lung volume that is not participating well in the gas transfer process.
  • the determined values for functional residual capacity for the breaths are displayed in graphic portion 110 of screen 102 g 2 as a capacity or volume curve 224 in steps 226 a , 226 b . . . 226 c at the end of the determination for each breath.
  • This confirms to the clinician that the determination of functional residual capacity is working properly.
  • curve 224 forms from left to right, the shape of the curve is an indication to the clinician of the intrinsic resistance and quality of ventilation of lung functional residual capacity, as discussed above.
  • the clinician can appreciate that patient 12 has a homogeneously ventilated lung volume, as indicated by the qualitative flatness of the functional residual capacity curve, with a lung capacity of about 2500 ml.
  • the scaling of graph 110 of FIG. 5 may be automatically altered to provide a scale appropriate to the functional residual capacity data being shown.
  • the data relating breath number to the corresponding functional residual capacity value can also be displayed in tabular form in portion 112 of display portion 102 g .
  • Mechanical ventilator 10 continues to supply breathing gases having increased oxygen concentration for x number of breaths, for example, 20 breaths.
  • a final value for functional residual capacity is determined at the end of the x breaths at step 228 and volume or capacity curve 224 extends to this breath to show the final determination of functional residual capacity at the end of 20 breaths.
  • the functional residual capacity measurement may conclude earlier if sufficient stability of breath-to-breath functional residual capacity is found in curve 224 .
  • step 230 the concentration of oxygen in the breathing gases is altered to the original level of, for example 50%, set at step 208 and ventilator 10 is operated at step 232 to repeat steps 216 - 228 to make a second determination of functional residual capacity with this alteration of the oxygen concentration in the breathing gases.
  • this determination uses a wash-in of nitrogen, rather than a wash-out.
  • This second determination is graphed and displayed in graphic portion 110 as graph 234 , in the same manner as graph 224 , described above.
  • the values for the two final functional residual capacity determinations are shown in data field 237 of tabular portion 112 of screen 102 g 2 in step 236 . In the example shown, these values are 2500 and 2550 ml.
  • step 232 the final determination of functional residual capacity made in step 232 is compared to that determined in step 228 . This is carried out at step 238 . It is then determined, in step 240 , whether the difference between the two determinations of functional residual capacity is less or greater than some amount, such as 25%. If the difference is less than 25%, the two values are averaged and will be subsequently displayed in text form in data field 245 in step 244 when determination becomes part of the chronological record following a later functional residual capacity determination.
  • some amount such as 25%
  • both the final value determined at step 228 and the final value determined in step 232 will be displayed by step 246 in data field 245 of FIG. 5 and in the graph 110 .
  • This display of the functional residual capacity determination informs the clinician that the accuracy of the functional residual capacity determination is questionable.
  • the final value(s) for the functional residual capacity are preferably displayed in tabular portion 112 of screen 102 g 2 along with additional associated data such as the time and date at which functional residual capacity was determined, or the values of PEEPe and PEEPi existing when the functional residual capacity determination was made.
  • PEEPe is the end expiratory pressure established by ventilator 10 .
  • PEEPi also known as auto PEEP, is the intrinsic end expiratory pressure and is a measurement in pressure of the volume of gas trapped in the lungs at the end of expiration to the PEEPe level.
  • steps 218 through 246 are repeated after the time interval indicated in data field 214 with the start of the functional residual capacity determination occurring at the time displayed in data field 248 .
  • the predetermined time interval may be overridden or the functional residual capacity determination terminated by appropriate commands from the clinician entered into menu 68 .
  • the volume curves, such as 224 , 234 , and functional residual capacity data, such as that in field 237 , generated in the course of successive functional residual capacity determinations are saved by ventilator display unit 76 and, as such, can be compared to data from previous or subsequent functional residual capacity determinations. This comparison requires that a previous determination of functional residual capacity be selected as a reference curve using the time at which it was obtained as identified in data field 250 . When a reference curve is selected, an indication is made in data field 250 and that functional residual capacity curve is displayed as the reference curve 252 . Curve 252 shows a lung that is not well ventilated.
  • Further indication of the reference curve and reference curve values may be made by a color indication for this data, different from that of the other functional residual capacity data in graph 110 and table 112 .
  • the result is a visual indicator that can easily be referred to by the clinician to quickly assess improvement or deterioration in the functional residual capacity condition of patient 12 over time.
  • FIG. 5 there has been an increase in the functional residual capacity of patient 12 for each eight hour interval.
  • Certain clinical or other events can affect the value for functional residual capacity determined from the method steps shown in FIG. 7 .
  • Such events may include performing a suction routine on patient 12 to remove accumulated secretions, administering a nebulized medication, changing the ventilation mode, or changing one or more ventilation parameters, such as tidal volume (TV), breath rate, PEEP, or other parameter.
  • tidal volume TV
  • breath rate PEEP
  • screen 102 g 4 of FIG. 8 will be shown to provide a log of the events that may effect functional residual capacity in data field 254 along with the time(s) and date(s) the event took place.
  • the log also includes the time, date and value of any periodic functional residual capacity determinations made in the manner described above.
  • the clinician may scroll through the events of the log using control knob 106 to review the functional residual capacity event history in relation to the measured values of functional residual capacity to determine if specific actions had a positive or negative effect on the determined functional residual capacity for the patient.
  • An aspect of the present invention allows the clinician to ascertain the relationship between the functional residual capacity of patient 12 , and PEEP applied to the patient, thereby to assist the clinician in establishing a PEEP level deemed optimal for patient 12 .
  • An optimal PEEP level in the present context, is one beyond which diminishing functional residual capacity increases in association with PEEP increases is noted.
  • the PEEP INview screen 102 g 5 of FIG. 9 may be used for this purpose.
  • a series of periodic functional residual capacity determinations is made, preferably in the manner shown in FIG. 7 , with each determination being at a different incremented level of PEEP.
  • the clinician sets an altered concentration of oxygen to be used in the functional residual capacity determination in data field 400 .
  • the clinician also enters an initial PEEP value at data field 402 and an end PEEP value at data field 404 .
  • the initial PEEP value may be low and the end value high, as shown in FIG. 9 , or the initial value high and the end value low.
  • the clinician also sets the number of functional residual capacity measurements to be made between the initial and end PEEP values in data field 406 . In the example shown in FIG. 9 , five such measurements are to be made.
  • the incremental PEEP associated with each measurement for example an incremental change of 3 cmH 2 O for each measurement, may be set. While use of the method of determining functional residual capacity of FIG. 7 is described below, it will be appreciated, that for the purpose of determining a suitable PEEP, any method of determining functional residual capacity may be employed.
  • Curve 408 and table 112 provide guidance to the clinician in selecting a PEEP level for ventilating patient 12 .
  • a PEEP level for ventilating patient 12 For example, from the graph and table of FIG. 9 it can be seen that increasing the PEEP from 2 to 6 cmH 2 O increases functional residual capacity by 500 ml whereas increasing PEEP beyond 6 cmH 2 O provides a relatively small increase in functional residual capacity. This suggests to the clinician that 6 cmH 2 O would be an appropriate PEEP for the patient.
  • Curve 408 can be saved in a memory in ventilator 10 or display unit 76 . If ventilator settings are not changed or are not changed in any significant way, curves 408 obtained at different times in the course of the patient's treatment can be usefully presented in graphic portion 110 of screen 102 g to enable the clinician to note changes in the PEEP curve over time by comparing the data of two or more curves 408 over time.
  • the respiration rate or the related quantities of expiration time and inspiratory:expiratory (I:E) ratio, can affect functional residual capacity primarily through the mechanism of intrinsic PEEP. Determining and displaying the relationship of one or more of these quantities to functional residual capacity may be useful to a clinician.
  • the functional residual capacity of the lungs 38 of patient 12 can be determined at differing respiration rates and the data displayed in graphic or tabular form to show the relationship between functional residual capacity and respiration rate.
  • the abscissa would show the respiration rate while the abscissa continues to show functional residual capacity.
  • a tabular presentation comprises a column of respiration rates and a column of corresponding functional residual capacity determinations.
  • FIG. 9B shows an example of a further manner of obtaining and displaying functional residual capacity and PEEP data.
  • the abscissa presents PEEP and the ordinate presents the change in functional residual capacity volume for a given change in PEEP, or ⁇ FRC/ ⁇ PEEP.
  • the relationship between changes in lung volume and changes in lung pressure is termed the “compliance” of the lung.
  • the presentation of changes in functional residual capacity volume, ⁇ FRC, to changes in PEEP, ⁇ PEEP, in FIG. 9B as compliance properties of the lung serves to emphasize clinically important data presented in graphic and textual form in FIG. 9 and to aid the clinician in selecting an appropriate PEEP for the patient.
  • the ordinate of graph 110 in FIG. 9B is labeled as compliance.
  • the data in FIG. 9 presented in the manner of FIG. 9B shows that the incremental 2 cmH 2 O pressure increase in PEEP from 2 to 4 cmH 2 O PEEP produced a functional residual capacity volume increase of 200 ml, giving a compliance of 100 ml/cmH 2 O, as graphically shown in FIG. 9B at the left hand point in the graph.
  • the incremental 2 cmH 2 O PEEP increase from 4 to 6 cmH 2 O PEEP produced a functional residual capacity volume increase of 300 ml, giving a compliance of 150 ml/cmH 2 O at the second point, proceeding to the right in the graph of FIG. 9B .
  • Corresponding determinations are made for the incremental PEEP increases from 6 to 8 and from 8 to 10 cmH 2 O and shown by the remaining points in FIG. 9B .
  • the data may also be presented in tabular form in table 112 of FIG. 9B .
  • screen 102 g 5 of FIG. 9 provides valuable insight and information to the clinician, it may also be helpful for the clinician to have a better idea of how much of an increase in functional residual capacity is due to distension of the lung by increased PEEP and how much is due to making previously closed alveolar sacs available, i.e., opening of the lung by “recruitment” of lung volume.
  • PEEP INview screen 102 g 5 of FIG. 9 One way such information may be obtained using the PEEP INview screen 102 g 5 of FIG. 9 is as follows. Functional residual capacity is determined for a series of PEEPs, in the manner described above to produce a curve, such as curve 408 . Thereafter a recruitment maneuver is carried out on patient 12 to open the alveolar sacs of the lungs of the patient. This would ordinarily be the provision of a high level of PEEP that, while it may only be tolerated by a patient for a short period of time, serves to open the alveolar sacs of the patient lungs. This is ordinarily carried out by the clinician by operating ventilator 10 independently of screen 102 g 5 . For this maneuver, it is preferable to use a recruitment PEEP greater than the highest PEEP set in menu 108 of screen 102 g 5 to ensure the alveolar sacs open.
  • the functional residual capacity is again determined for the same series of PEEPs used prior to performing the recruitment maneuver to produce another curve 408 a .
  • the two curves can be displayed in graphic portion 110 of screen 102 g 5 in the manner shown in FIG. 9A . If the recruitment maneuver resulted in the recruitment of lung volume, i.e. in the opening of previously closed alveolar sacs, curve 408 a will show a higher functional residual capacity than curve 408 , as shown in FIG. 9A . Curves 408 and 408 a will tend to come together at the PEEP level at which de-recruitment of lung volume begins to occur. This suggests to the clinician that a PEEP level greater than one at which de-recruitment begins to occur would be appropriate for the patient.
  • spirometry is used to determine the mechanics of a patient's lungs by examining relationships between breathing gas flows, volumes, and pressures during a breath of a patient.
  • a commonly used relationship is that between inspired/expired breathing gas flows and volumes that, when graphed, produces a loop spirogram. The size and shape of the loop is used to diagnose the condition of the lung.
  • pressure has been measured at a point removed from the lungs so that the measured pressure may not be an accurate reflection of actual pressure in the lungs thus lessening the diagnostic value of the pressure-volume loop.
  • catheter 94 extending from endotracheal tube 90 shown in FIG. 2 .
  • a far more accurate indication of lung pressure is obtained.
  • a graph of the relationship between volume and pressure is roughly an elongated, narrow loop of positive uniform slope. That is, constant increments of inspired volume increase lung pressure by constant increments. The loop is formed because there remains some amount of lung resistance below the pressure sensing point at the end of catheter 94 .
  • the loop may be wider and may also reflect a non-linear lung volume pressure relationship.
  • the volume-pressure relationship over the course of an inspiration/expiration may be in a form such as that shown in FIG. 10 by 420 , and a curve illustrating the volume-pressure relationship resulting from a mathematical computation using loop data is plotted, as shown in FIG. 10 by reference numeral 422 .
  • the curve 422 shown in FIG. 10 in often termed a “dynostatic curve” and is used for diagnostic purposes.
  • a typical dynostatic curve is shown in FIG. 10 to contain a middle portion of somewhat linear positive slope and a pair of inflection points separating end portions of differing slopes.
  • the abscissa of the graph is lung pressure measured at the end of catheter 94 connected to the auxiliary input A of ventilator display unit 76 and is termed “Paux”.
  • the ordinate is scaled in volume of breathing gases inspired/expired by patient 12 . It will be appreciated that this volume comprises the tidal volume for the patient.
  • the tidal volume moves into and out of the lungs in a manner that can be described as being “above” the functional residual capacity. That is, for normal breathing, a patient starts a breath with the volume of the lungs at the functional residual capacity which may, for example be 2000 ml.
  • the volume of the lungs increases by the tidal volume of, for example 500-700 ml, and during exhalation, the volume of the lungs decreases by approximately that amount.
  • a mechanical ventilator such as ventilator 10 .
  • the ordinate of the graph 110 in FIG. 10 is scaled in the relative volume of inspiration/expiration for which the origin of the graph is zero, not in absolute volume that would also take into consideration functional residual capacity and for which the origin of a graph would be the amount of the functional residual capacity.
  • the scaling of graph 110 of FIG. 10 may be automatically altered to provide a scale appropriate to the spirometry data being shown.
  • the menu portion 108 of SpiroD screen 102 g 3 shown in FIG. 10 allows the user to open up a set up menu, shown in FIG. 11 that allows the clinician to turn a purge flow through catheter 94 on or off or to zero the Paux sensor connected to catheter 94 when the purge flow is on and endotracheal tube 90 has been inserted in patient 12 .
  • the SpiroD set-up menu also allows the clinician to set the scaling for the graphical portions of the display.
  • a “Paux Alarm” screen, reached from the SpiroD setup screen of FIG. 11 allows the clinician to set appropriate alarms for patient lung pressure, as sensed by catheter 94 .
  • Various other selections on menu 108 of screen 102 g 3 of FIG. 10 allow the clinician to save the current data and to view this information as a first or second reference for use and display with subsequently obtained data. Up to a given number of loops, for example, six loops and curves, may be saved for analytical purposes.
  • the “erase reference” option allows the user to determine which information to save and which to delete.
  • the “SpiroD loops” and “SpiroD curves” menu items may be turned on or off. Selecting “on” for both the curve and loop will display both the loop and the curve at once in the manner shown in FIG. 10 . For easier comparison among loops and curves obtained at various times, either the loop or curve showing may be turned “off.”
  • the “cursor” option allows the clinician to scroll along the horizontal axis and display the actual pressure and volume measurements associated with the loops or curves that are displayed.
  • volume and pressures are obtained from sensor 57 and catheter 94 and the spirometry data, computed and displayed for every third breath if the respiratory rate is less than some desired number, for example, 15 breaths per minute. If the respiratory rate is greater than that number, every fifth breath used.
  • the loop 420 for a complete inspiratory/expiratory breathing cycle is displayed in the graph of screen 102 g 3 of FIG. 10 .
  • the dynostatic curve 422 is then calculated for display in graph 110 .
  • Compliance can be seen as the amount by which the volume of the lung increases for an incremental increase in lung pressure.
  • the data necessary to determine compliance can be obtained from sensor 57 and gas module 64 .
  • Compliance is represented by the slope of dynostatic curve 422 . It is an indication of the stiffness or elasticity of the lung. In a stiff lung, an incremental increase in pressure results in a smaller increase in volume over a lung that is more elastic and the slope of curve 422 is more horizontal. In an elastic lung, the reverse is true. To aid the clinician in analyzing the lungs of patient 10 , the compliance is computed at the beginning, middle, and end of the respiratory cycle of the patient.
  • the middle portion of dynostatic curve 422 indicates a portion of greater compliance than the end portions. This is reflected in the greater slope of the middle portion over those of the end portions.
  • the table of the screen sets out numerical values. Ordinarily, the highly compliant, middle portion of curve 422 shown in FIG. 10 is that in which the lung is most effectively ventilated.
  • the table 112 of display 102 g 3 of FIG. 10 also shows the peak pressure achieved in the lungs during the breath, the PEEP pressure, and the airway resistance, Raw.
  • the airway resistance is the pressure drop experienced by breathing gas flow of the lungs and is expressed in units of pressure per unit of flow. Airway resistance can also be determined with data from sensor 57 and gas module 64 in a manner described in the Stenqvist reference noted above.
  • the present invention provides a unique way of viewing the relationship among functional residual capacity, PEEP, and recruited:de-recruited lung volume that is deemed helpful in enabling a clinician to determine a suitable value for PEEP.
  • the PEEP INview screen 102 g 5 shown in FIG. 9 is reached.
  • the menu items present in PEEP INview screen 102 g 5 is “Lung INview on/off” in field 424 .
  • a screen 102 g 6 in the format of FIGS. 12 a and 12 b is present in ventilator display unit 76 .
  • the menu item “Lung INview on/off” 424 is toggled “on” and the ventilator display unit will show screen 102 g 6 in the format of FIGS. 12 a and 12 b.
  • the clinician sets the altered oxygen level to be used in the functional residual capacity measurement employed to produce the Lung INview data.
  • the clinician establishes initial and end PEEPs values at fields 432 and 434 , as well as the number of measurements to be taken within the range of PEEP so established at field 436 , in the same general manner as described above in connection with the PEEP INview display 102 g 5 of FIG. 9 .
  • field 436 can show the incremental/decremental PEEP step, for example a step of 3 cmH 2 O.
  • the initial PEEP is 25 cmH 2 O
  • the end PEEP is 5 cmH 2 O
  • five measurements will be taken within that range of PEEP, namely measurements at 25, 20, 15, 10, and 5 cmH 2 O of PEEP. It is deemed preferable to initiate the process of determining the optimal PEEP by using the highest value of the selected range and thereafter decrementing the applied PEEP to the lower end level.
  • the invention can also be practiced with incrementing PEEP from a low value to a high value, depending on the preference of the clinician.
  • the graph 110 of screen 102 g 6 of FIG. 12 has the abscissa scaled in PEEP and the ordinate scaled in functional residual capacity.
  • the table 112 of screen 102 g 6 provides columns for the set PEEP, functional residual capacity and airway resistance (Raw).
  • the table also includes a column for “difference” that, as hereinafter described, contains a numerical indication of the lung volume that is recruited/de-recruited in the lungs as the PEEP is incremented/decremented.
  • a recruitment maneuver is preferably run on patient 12 to open the lungs of the patient.
  • such recruitment maneuver would typically be the provision of a high level of PEEP opens the alveolar sacs of the patient lungs. It is preferable to use a recruitment PEEP greater than the highest PEEP set in menu 108 of screen 102 g 6 to ensure the alveolar sacs open.
  • the functional residual capacity and PEEP parameters are established in menu 108 of display 102 g 6 , shown in FIG. 12 , as previously described. Step 502 may occur before step 500 reversing the order shown in FIG. 13 .
  • the patient is ventilated by ventilator 10 with the PEEP at the initial level found in the menu. In the present exemplary instance, patient 12 is initially ventilated with a PEEP of 25 cmH 2 O in step 504 .
  • the functional residual capacity of patient 12 is determined by the wash in/wash out technique using the altered oxygen concentration level as described above in connection with FIGS. 5 and 7 or using some other appropriate technique for measuring functional residual capacity.
  • the determined value is graphically displayed in graph 110 at the corresponding value of PEEP as point 508 .
  • the values are also entered in tabular form in table 112 of screen 102 g 6 of FIG. 12 .
  • step 512 the functional residual capacity is again determined and displayed with respect to PEEP in the same manner as in step 506 at point 514 .
  • Curve 516 is formed in graph 110 from points 508 and 514 .
  • FIG. 14 shows the spirometry data obtained at step 518 for the PEEP of 20 cmH 2 O.
  • the spirometry loop is shown simply as an ellipse 520 and dynostatic curve 522 shown as a straight line, it being understood that the spirometry loops and curves will actually resemble those shown in FIG. 10 .
  • the ordinate of the graph of FIG. 14 is scaled in absolute volume, not the relative volume of FIG. 10 , so as to show functional residual capacity, as noted in steps 506 and 512 .
  • the origin for dynostatic curve 522 will be the PEEP value of 20 cmH 2 O and the associated functional residual capacity value so that the origin corresponds to point 514 of FIG. 12 and FIG. 14 .
  • FIG. 14 can be seen as an enlargement of FIG. 12 showing the data used to generate the data of FIG. 12 and also showing dynostatic loops and curves.
  • FIG. 14 shows a significant amount of data relating to the condition of the lungs of patient 12 .
  • the graph 110 of screen 102 g 6 of FIG. 12 shows the salient features of that data, thereby to assist and facilitate the selection of an optimal PEEP for patient 12 by the clinician.
  • Steps 510 , 512 and 518 are then repeated for the next decremented PEEP of 15 cmH 2 O. This produces a new point 530 of functional residual capacity and PEEP in curve 516 in FIGS. 12 a and 12 b and in FIG. 14 . It also produces a new spirometry loop and dynostatic curve 532 . Steps 510 , 512 , and 518 are again repeated for a PEEP of 10 cmH 2 O to produce point 534 and dynostatic curve 536 shown in FIG. 14 .
  • Steps 524 , 526 and 528 are used to determine the amount of recruited or de-recruited volume obtained in the lungs of patient 12 .
  • PEEPs of 15 and 10 cmH 2 O some de-recruitment of lung volume is noted and steps 524 , 526 and 528 of FIG. 13 are explained in conjunction with these PEEPs.
  • step 524 and using the dynostatic curve 536 for the reduced PEEP of 10 cmH 2 O the volume of the lungs at a pressure corresponding to that of the previous PEEP of 15 cmH 2 O is determined. Graphically, this may be accomplished by establishing vertical line 538 in of FIG. 14 at the previous PEEP of 15 cmH 2 O and noting the intersection of line 538 and dynostatic curve 536 at point 540 .
  • step 528 The amount of volume on the ordinate scale represented by the line segment 538 a between points 530 and 540 is also determined. In the present instance, this amounts to approximately 180 ml.
  • this value is placed in table 112 of screen 102 g 6 in association with the previous PEEP of 15 cmH 2 O.
  • point 540 is placed in graph 110 of screen 102 g 5 as shown in FIGS. 12 a and 12 b.
  • FIG. 12 b shows the completed Lung INview process, including the final measurement of functional residual capacity at a PEEP of 5 cmH 2 O. This is carried out by repeating steps 510 , 512 , and 518 , for a PEEP of 5 cmH 2 O to produce plot 542 of functional residual capacity and PEEP and dynostatic curve 544 . Repeating steps 524 , 526 , and 528 produces point 546 and line segment 548 a representing a volume of about 120 ml. The data is displayed in a manner corresponding to that described above in graph 110 and table 112 of screen 102 g 6 .
  • dynostatic curve 532 generated for the PEEP of 15 cmH 2 O. That is, dynostatic curve 532 passes through point 514 formed using the functional residual capacity for 20 cmH 2 O. Again, there is a zero difference as tabulated in table 112 for 20 cmH 2 O. In graph 110 of FIGS. 12 a and 12 b , where the difference approximates zero, the differences determined in step 528 and the plot of the functional residual capacity at the previous PEEP are roughly the same and overlapping.
  • point 530 shows that for a PEEP of 15 cmH 2 O, when the lung pressure is at that level, the lung volume is about 1800 ml. But when the PEEP is lowered to 10 cmH 2 O, for a pressure in the lungs of 15 cmH 2 O, the lung volume is only about 1620 ml, as evidenced by the plot of point 540 . There has thus been a lung volume de-recruitment of approximately 180 ml when the PEEP was lowered from 15 cmH 2 O to 10 cmH 2 O, as evidenced by the length of line segment 538 a.
  • a clinician may readily discern an optimal PEEP for patient 12 from the graphic and tabular data provided in screen 102 g 6 of FIG. 12 b .
  • the alveolar sacs will remain generally open during breathing due to the higher pressures. While this is advantageous from the standpoint of lung volume, the high pressure may be injurious to the patient. There is little reduction, or de-recruitment of lung volume as expiration proceeds to the end expiratory pressure, as shown in FIG. 12 .
  • the lung begins to lose volume or “derecruits” at PEEP settings below 15 cmH 2 O and this suggests that 15 cmH 2 O is a PEEP that is best suited or optimal for patient 12 .
  • the clinician may set the PEEP at 15 cmH 2 O so as to obtain some recruitment of lung volume over a PEEP of 10 cmH 2 O. This may be preceded by a recruitment maneuver, such as at step 500 , if desired. Or, the clinician may leave the PEEP at 10 cmH 2 O since some recruitment is obtained at that level of PEEP.
  • the determination of a suitable PEEP can be set to automatically occur in conjunction with certain procedures carried out by ventilator 10 or treatment procedures carried out on patient 12 .

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Cited By (56)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070113849A1 (en) * 2005-11-21 2007-05-24 Ric Investments, Llc. System and method of monitoring respiratory events
US20080302363A1 (en) * 2007-06-05 2008-12-11 Allied Healthcare Products, Inc. Ventilator apparatus
US20090020120A1 (en) * 2007-07-20 2009-01-22 Map Medizin-Technologie Gmbh Monitor for CPAP/ventilator apparatus
US20090183737A1 (en) * 2008-01-22 2009-07-23 The General Electric Company Pulse width modulated medical gas concentration control
US20090241956A1 (en) * 2008-03-27 2009-10-01 Nellcor Puritan Bennett Llc Method for controlling delivery of breathing gas to a patient using multiple ventilation parameters
US20090241958A1 (en) * 2008-03-27 2009-10-01 Nellcor Puritan Bennett Llc Method for selecting target settings in a medical device
WO2010022513A1 (en) * 2008-08-28 2010-03-04 Maquet Critical Care Ab Determining patient- ventilator breath contribution index in spontaneously breathing, mechanically ventilated patients
WO2010031125A1 (en) 2008-09-17 2010-03-25 Resmed Ltd Display and controls for a cpap device
US20100229867A1 (en) * 2007-11-05 2010-09-16 Resmed Limited Ventilation system and control thereof
US20110132369A1 (en) * 2009-12-04 2011-06-09 Nellcor Puritan Bennett Llc Ventilation System With System Status Display
USD645158S1 (en) 2010-04-27 2011-09-13 Nellcor Purtian Bennett LLC System status display
US20110284007A1 (en) * 2010-05-21 2011-11-24 Pierre Peron Positive pressure device
US20110308518A1 (en) * 2009-02-13 2011-12-22 Koninklijke Philips Electronics N.V. Pressure support device user interface
CN102369036A (zh) * 2009-03-27 2012-03-07 马奎特紧急护理公司 呼吸设备的peep调节
KR101138958B1 (ko) 2010-02-17 2012-04-25 주식회사 멕 아이씨에스 인공 호흡기의 유속 방향 조절 장치
US20120138057A1 (en) * 2010-12-06 2012-06-07 General Electric Company System and Method of Automated Lung Recruitment Maneuvers
US8335992B2 (en) 2009-12-04 2012-12-18 Nellcor Puritan Bennett Llc Visual indication of settings changes on a ventilator graphical user interface
US20130032149A1 (en) * 2011-08-04 2013-02-07 General Electric Company Method and system for visualizing mechanical ventilation information
US8443294B2 (en) 2009-12-18 2013-05-14 Covidien Lp Visual indication of alarms on a ventilator graphical user interface
US8453643B2 (en) 2010-04-27 2013-06-04 Covidien Lp Ventilation system with system status display for configuration and program information
US8453645B2 (en) 2006-09-26 2013-06-04 Covidien Lp Three-dimensional waveform display for a breathing assistance system
US20130174846A1 (en) * 2010-06-19 2013-07-11 The Lung Barometry Sweden Ab C/O Stenqvist System and method for determination of transpulmonary pressure in a patient connected to a breathing apparatus
US8511306B2 (en) 2010-04-27 2013-08-20 Covidien Lp Ventilation system with system status display for maintenance and service information
US8539949B2 (en) 2010-04-27 2013-09-24 Covidien Lp Ventilation system with a two-point perspective view
US8555882B2 (en) 1997-03-14 2013-10-15 Covidien Lp Ventilator breath display and graphic user interface
US8597198B2 (en) 2006-04-21 2013-12-03 Covidien Lp Work of breathing display for a ventilation system
US8695591B2 (en) 2010-05-26 2014-04-15 Lloyd Verner Olson Apparatus and method of monitoring and responding to respiratory depression
CN103813825A (zh) * 2011-09-22 2014-05-21 皇家飞利浦有限公司 用于监测和控制压力支持设备的方法与装置
US8844526B2 (en) 2012-03-30 2014-09-30 Covidien Lp Methods and systems for triggering with unknown base flow
US8924878B2 (en) 2009-12-04 2014-12-30 Covidien Lp Display and access to settings on a ventilator graphical user interface
US9022031B2 (en) 2012-01-31 2015-05-05 Covidien Lp Using estimated carinal pressure for feedback control of carinal pressure during ventilation
US9119925B2 (en) 2009-12-04 2015-09-01 Covidien Lp Quick initiation of respiratory support via a ventilator user interface
USD741879S1 (en) * 2012-07-30 2015-10-27 General Electric Company Display screen or portion thereof with graphical user interface
US9262588B2 (en) 2009-12-18 2016-02-16 Covidien Lp Display of respiratory data graphs on a ventilator graphical user interface
US9364624B2 (en) 2011-12-07 2016-06-14 Covidien Lp Methods and systems for adaptive base flow
US9492629B2 (en) 2013-02-14 2016-11-15 Covidien Lp Methods and systems for ventilation with unknown exhalation flow and exhalation pressure
US9498589B2 (en) 2011-12-31 2016-11-22 Covidien Lp Methods and systems for adaptive base flow and leak compensation
USD775345S1 (en) 2015-04-10 2016-12-27 Covidien Lp Ventilator console
US9649458B2 (en) 2008-09-30 2017-05-16 Covidien Lp Breathing assistance system with multiple pressure sensors
US9713689B2 (en) 2010-07-12 2017-07-25 Laurent Brochard Methods of evaluating a patient for PEEP therapy
US9808591B2 (en) 2014-08-15 2017-11-07 Covidien Lp Methods and systems for breath delivery synchronization
CN107405107A (zh) * 2015-03-17 2017-11-28 弗里茨·斯蒂芬医疗技术有限责任公司 呼吸器及其控制方法
US9925346B2 (en) 2015-01-20 2018-03-27 Covidien Lp Systems and methods for ventilation with unknown exhalation flow
US9950129B2 (en) 2014-10-27 2018-04-24 Covidien Lp Ventilation triggering using change-point detection
US20180140793A1 (en) * 2015-05-25 2018-05-24 The Lung Barometry Sweden AB Method, system and software for protective ventilation
US9981096B2 (en) 2013-03-13 2018-05-29 Covidien Lp Methods and systems for triggering with unknown inspiratory flow
US20190125994A1 (en) * 2017-10-27 2019-05-02 OrangeMed, Inc. Ventilators and systems for performing automated ventilation procedures
US10362967B2 (en) 2012-07-09 2019-07-30 Covidien Lp Systems and methods for missed breath detection and indication
US20200038610A1 (en) * 2016-12-20 2020-02-06 Koninklijke Philips N.V. Determining respiratory mechanic parameters in the presence of intrinsic positive end-expiratory pressure
US10617835B2 (en) * 2007-02-17 2020-04-14 Drägerwerk AG & Co. KGaA Patient connection for the artificial respiration of a patient
CN111712290A (zh) * 2018-02-12 2020-09-25 提姆佩尔医疗有限责任公司 用于确定患者对肺泡复张手法的应答性的系统和方法
US10905838B2 (en) * 2015-09-03 2021-02-02 Hamilton Medical Ag Ventilator with error detection for flow sensors
US20220096765A1 (en) * 2019-01-29 2022-03-31 Drägerwerk AG & Co. KGaA Ventilation apparatus and ventilation method
US11324954B2 (en) 2019-06-28 2022-05-10 Covidien Lp Achieving smooth breathing by modified bilateral phrenic nerve pacing
US11672934B2 (en) 2020-05-12 2023-06-13 Covidien Lp Remote ventilator adjustment
US12257437B2 (en) 2020-09-30 2025-03-25 Covidien Lp Intravenous phrenic nerve stimulation lead

Families Citing this family (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2007510504A (ja) 2003-11-12 2007-04-26 ドレーガー　メディカル　システムズ　インコーポレイテッド 保健医療処理装置および表示システム
WO2008148134A1 (en) * 2007-06-01 2008-12-04 Intensive Care On-Line Network, Inc. Ventilator apparatus and system for ventilation
EP2276403A4 (en) * 2008-04-23 2012-11-07 Inca Medical Systems Ltd DETERMINATION OF THE FUNCTIONAL RESTACTION CAPACITY
US20100095964A1 (en) * 2008-10-20 2010-04-22 General Electric Company method and system for synchronizing a patient monitoring device with a ventilator device
JP5695573B2 (ja) * 2008-12-09 2015-04-08 コーニンクレッカ フィリップス エヌ ヴェ 被験者の機能的残気量の決定のためのシステムおよび方法
US8408203B2 (en) * 2009-04-30 2013-04-02 General Electric Company System and methods for ventilating a patient
US20110271960A1 (en) * 2010-05-07 2011-11-10 Nellcor Puritan Bennett Llc Ventilator-Initiated Prompt Regarding Auto-PEEP Detection During Volume Ventilation Of Triggering Patient
US8607791B2 (en) 2010-06-30 2013-12-17 Covidien Lp Ventilator-initiated prompt regarding auto-PEEP detection during pressure ventilation
DE102011018671B4 (de) * 2011-04-27 2017-12-14 Drägerwerk AG & Co. KGaA Mobiles Beatmungsgerät
CN104411355B (zh) 2012-05-02 2017-11-03 费雪派克医疗保健有限公司 呼吸加湿器通信系统和方法
EP2919650A4 (en) * 2012-11-19 2016-07-27 Gen Hospital Corp SYSTEM AND METHOD FOR MONITORING THE REPRODUCTION OR BREATHING MECHANISM OF A PATIENT
HRP20170704T1 (hr) 2012-12-04 2017-10-06 Ino Therapeutics Llc Kanila za minimiziranje razrjeđenja doziranja za vrijeme isporuke dušikovog oksida
US9795756B2 (en) 2012-12-04 2017-10-24 Mallinckrodt Hospital Products IP Limited Cannula for minimizing dilution of dosing during nitric oxide delivery
US9839760B2 (en) * 2014-04-11 2017-12-12 Vyaire Medical Capital Llc Methods for controlling mechanical lung ventilation
US10905836B2 (en) 2015-04-02 2021-02-02 Hill-Rom Services Pte. Ltd. Manifold for respiratory device
US10758693B2 (en) * 2015-09-10 2020-09-01 St. Michael's Hospital. Method and system for adjusting a level of ventilatory assist to a patient
DE102017101645A1 (de) * 2017-01-27 2018-08-02 Ventinova Technologies B.V. Vorrichtungen und Verfahren zur Beatmung eines Patienten
WO2018153964A1 (en) 2017-02-22 2018-08-30 Koninklijke Philips N.V. Automatic peep selection for mechanical ventilation
JP7047574B2 (ja) * 2018-04-26 2022-04-05 コニカミノルタ株式会社 動態画像解析装置、動態画像解析システム、動態画像解析プログラム及び動態画像解析方法
CN111479605A (zh) * 2018-11-23 2020-07-31 深圳迈瑞生物医疗电子股份有限公司 一种呼气末正压确定方法及装置、通气设备、存储介质

Citations (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4307730A (en) * 1979-03-29 1981-12-29 Siemens Aktiengesellschaft Apparatus for pulmonary function analysis
US4333476A (en) * 1978-12-15 1982-06-08 Downing Jr Willis G Comprehensive pulmonary measurement technique
US5088332A (en) * 1988-12-12 1992-02-18 Instrumentarium Corporation Gas flow restricting and directing device intended for flow measurement
US5513647A (en) * 1994-05-03 1996-05-07 Childrens Hospital Inc Method for measuring adult-type pulmonary function tests in sedated infants and apparatus therefor
US5540233A (en) * 1993-10-22 1996-07-30 Siemens-Elema Ab Method for determining the functional residual capacity of lungs and a ventilator for practicing said method
US5575283A (en) * 1994-02-14 1996-11-19 Siemens-Elema Ab Device for determining an opening pressure in the lungs
US5615669A (en) * 1994-07-22 1997-04-01 Siemens Elema Ab Gas mixture and device for delivering the gas mixture to the lungs of a respiratory subject
US5660170A (en) * 1995-06-02 1997-08-26 Burkhard Lachmann Respiratory apparatus and method for determining an optimal opening pressure in a lung system
US5915381A (en) * 1995-12-01 1999-06-29 Siemens Elema Ab Breathing apparatus and method for controlling same
US5937854A (en) * 1998-01-06 1999-08-17 Sensormedics Corporation Ventilator pressure optimization method and apparatus
US5957128A (en) * 1996-02-21 1999-09-28 Hecker; Karl-Heinz Method and device for determination of the functional residual capacity (FRC)
US6135105A (en) * 1995-10-20 2000-10-24 University Of Florida Lung classification scheme, a method of lung class identification and inspiratory waveform shapes
US6139506A (en) * 1999-01-29 2000-10-31 Instrumentarium Oy Method for measuring pulmonary functional residual capacity
US6158432A (en) * 1995-12-08 2000-12-12 Cardiopulmonary Corporation Ventilator control system and method
US6273855B1 (en) * 1998-05-14 2001-08-14 B. Braun Melsungen Ag Method and device for compressed optical representation of medical data
US6306099B1 (en) * 2000-02-17 2001-10-23 Board Of Trustees Of The University Of Arkansas Method of measuring residual lung volume in infants
US6315739B1 (en) * 1999-09-27 2001-11-13 Instrumentarium Corporation Apparatus and method for measuring the intratracheal pressure of an intubated patient
US6544191B2 (en) * 2000-09-20 2003-04-08 DRäGER MEDIZINTECHNIK GMBH Process for determining the functional residual capacity of the lungs
US20040003813A1 (en) * 1999-06-30 2004-01-08 Banner Michael J. Medical ventilator and method of controlling same
US6709405B2 (en) * 2001-09-25 2004-03-23 Siemens Elema Ab Breathing apparatus and method for operation thereof for examining pulmonary mechanics of a respiratory system
US6840241B2 (en) * 2002-09-25 2005-01-11 Maquet Critical Care Ab Apparatus for determination of recruitable volume of a lung
US7465275B2 (en) * 2001-05-29 2008-12-16 Ge Healthcare Finland Oy Method and apparatus for measuring functional residual capacity (FRC) and cardiac output(CO)
US7681574B2 (en) * 2005-12-22 2010-03-23 General Electric Company Method and apparatus for determining functional residual capacity of the lungs

Family Cites Families (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH06311979A (ja) * 1993-04-30 1994-11-08 I Vision:Kk 機能的残気量測定法
JPH0715537A (ja) * 1993-06-25 1995-01-17 Nitsuko Corp Ｉｓｄｎテレコントロールシステム
SE501074C2 (sv) * 1993-07-22 1994-11-07 Siemens Elema Ab Gasblandning och apparat för att tillföra gasblandningen till lungorna hos ett levande väsen
US20060211950A1 (en) * 2001-10-30 2006-09-21 Brunner Josef X Pressure-volume curve monitoring device
US7530353B2 (en) * 2005-09-21 2009-05-12 The General Electric Company Apparatus and method for determining and displaying functional residual capacity data and related parameters of ventilated patients

Patent Citations (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4333476A (en) * 1978-12-15 1982-06-08 Downing Jr Willis G Comprehensive pulmonary measurement technique
US4307730A (en) * 1979-03-29 1981-12-29 Siemens Aktiengesellschaft Apparatus for pulmonary function analysis
US5088332A (en) * 1988-12-12 1992-02-18 Instrumentarium Corporation Gas flow restricting and directing device intended for flow measurement
US5540233A (en) * 1993-10-22 1996-07-30 Siemens-Elema Ab Method for determining the functional residual capacity of lungs and a ventilator for practicing said method
US5575283A (en) * 1994-02-14 1996-11-19 Siemens-Elema Ab Device for determining an opening pressure in the lungs
US5513647A (en) * 1994-05-03 1996-05-07 Childrens Hospital Inc Method for measuring adult-type pulmonary function tests in sedated infants and apparatus therefor
US5615669A (en) * 1994-07-22 1997-04-01 Siemens Elema Ab Gas mixture and device for delivering the gas mixture to the lungs of a respiratory subject
US5660170A (en) * 1995-06-02 1997-08-26 Burkhard Lachmann Respiratory apparatus and method for determining an optimal opening pressure in a lung system
US6135105A (en) * 1995-10-20 2000-10-24 University Of Florida Lung classification scheme, a method of lung class identification and inspiratory waveform shapes
US5915381A (en) * 1995-12-01 1999-06-29 Siemens Elema Ab Breathing apparatus and method for controlling same
US6158432A (en) * 1995-12-08 2000-12-12 Cardiopulmonary Corporation Ventilator control system and method
US5957128A (en) * 1996-02-21 1999-09-28 Hecker; Karl-Heinz Method and device for determination of the functional residual capacity (FRC)
US5937854A (en) * 1998-01-06 1999-08-17 Sensormedics Corporation Ventilator pressure optimization method and apparatus
US6273855B1 (en) * 1998-05-14 2001-08-14 B. Braun Melsungen Ag Method and device for compressed optical representation of medical data
US6139506A (en) * 1999-01-29 2000-10-31 Instrumentarium Oy Method for measuring pulmonary functional residual capacity
US20040003813A1 (en) * 1999-06-30 2004-01-08 Banner Michael J. Medical ventilator and method of controlling same
US6315739B1 (en) * 1999-09-27 2001-11-13 Instrumentarium Corporation Apparatus and method for measuring the intratracheal pressure of an intubated patient
US6306099B1 (en) * 2000-02-17 2001-10-23 Board Of Trustees Of The University Of Arkansas Method of measuring residual lung volume in infants
US6544191B2 (en) * 2000-09-20 2003-04-08 DRäGER MEDIZINTECHNIK GMBH Process for determining the functional residual capacity of the lungs
US7465275B2 (en) * 2001-05-29 2008-12-16 Ge Healthcare Finland Oy Method and apparatus for measuring functional residual capacity (FRC) and cardiac output(CO)
US6709405B2 (en) * 2001-09-25 2004-03-23 Siemens Elema Ab Breathing apparatus and method for operation thereof for examining pulmonary mechanics of a respiratory system
US6840241B2 (en) * 2002-09-25 2005-01-11 Maquet Critical Care Ab Apparatus for determination of recruitable volume of a lung
US7681574B2 (en) * 2005-12-22 2010-03-23 General Electric Company Method and apparatus for determining functional residual capacity of the lungs

Cited By (103)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8555882B2 (en) 1997-03-14 2013-10-15 Covidien Lp Ventilator breath display and graphic user interface
US8555881B2 (en) 1997-03-14 2013-10-15 Covidien Lp Ventilator breath display and graphic interface
US20070113849A1 (en) * 2005-11-21 2007-05-24 Ric Investments, Llc. System and method of monitoring respiratory events
US8025052B2 (en) * 2005-11-21 2011-09-27 Ric Investments, Llc System and method of monitoring respiratory events
US8597198B2 (en) 2006-04-21 2013-12-03 Covidien Lp Work of breathing display for a ventilation system
US10582880B2 (en) 2006-04-21 2020-03-10 Covidien Lp Work of breathing display for a ventilation system
US8453645B2 (en) 2006-09-26 2013-06-04 Covidien Lp Three-dimensional waveform display for a breathing assistance system
US10617835B2 (en) * 2007-02-17 2020-04-14 Drägerwerk AG & Co. KGaA Patient connection for the artificial respiration of a patient
US8656913B2 (en) * 2007-06-05 2014-02-25 Allied Healthcare Products, Inc. Ventilator apparatus
US20080302363A1 (en) * 2007-06-05 2008-12-11 Allied Healthcare Products, Inc. Ventilator apparatus
US20090020120A1 (en) * 2007-07-20 2009-01-22 Map Medizin-Technologie Gmbh Monitor for CPAP/ventilator apparatus
US9072848B2 (en) * 2007-11-05 2015-07-07 Resmed Limited Ventilation system and control thereof
US20100229867A1 (en) * 2007-11-05 2010-09-16 Resmed Limited Ventilation system and control thereof
EP2217312A4 (en) * 2007-11-05 2017-12-06 ResMed Ltd. Ventilation system and control thereof
US10149952B2 (en) 2007-11-05 2018-12-11 Resmed Limited Continuous positive airway pressure device with user interface
US8789524B2 (en) * 2008-01-22 2014-07-29 General Electric Company Pulse width modulated medical gas concentration control
US20090183737A1 (en) * 2008-01-22 2009-07-23 The General Electric Company Pulse width modulated medical gas concentration control
US20090241957A1 (en) * 2008-03-27 2009-10-01 Nellcor Puritan Bennett Llc Breathing assistance systems with lung recruitment maneuvers
US8640700B2 (en) 2008-03-27 2014-02-04 Covidien Lp Method for selecting target settings in a medical device
US20090241956A1 (en) * 2008-03-27 2009-10-01 Nellcor Puritan Bennett Llc Method for controlling delivery of breathing gas to a patient using multiple ventilation parameters
US20090241958A1 (en) * 2008-03-27 2009-10-01 Nellcor Puritan Bennett Llc Method for selecting target settings in a medical device
US8640699B2 (en) 2008-03-27 2014-02-04 Covidien Lp Breathing assistance systems with lung recruitment maneuvers
US8720441B2 (en) 2008-08-28 2014-05-13 St. Michael's Hospital Determining patient-ventilator breath contribution index in spontaneously breathing, mechanically ventilated patients
WO2010022513A1 (en) * 2008-08-28 2010-03-04 Maquet Critical Care Ab Determining patient- ventilator breath contribution index in spontaneously breathing, mechanically ventilated patients
WO2010031125A1 (en) 2008-09-17 2010-03-25 Resmed Ltd Display and controls for a cpap device
US8944057B2 (en) 2008-09-17 2015-02-03 Resmed Limited Method and apparatus for controlling a CPAP device
EP2341969A4 (en) * 2008-09-17 2018-03-21 ResMed Ltd. Display and controls for a cpap device
US10046128B2 (en) 2008-09-17 2018-08-14 Resmed Limited Display and controls for a CPAP device
US20110164002A1 (en) * 2008-09-17 2011-07-07 Phoebe Katherine Hill Display and controls for a cpap device
US11298483B2 (en) 2008-09-17 2022-04-12 ResMed Pty Ltd Display and controls for a CPAP device
US9649458B2 (en) 2008-09-30 2017-05-16 Covidien Lp Breathing assistance system with multiple pressure sensors
US9844636B2 (en) * 2009-02-13 2017-12-19 Koninklijke Philips N.V. Pressure support device user interface
US20110308518A1 (en) * 2009-02-13 2011-12-22 Koninklijke Philips Electronics N.V. Pressure support device user interface
US9333312B2 (en) 2009-03-27 2016-05-10 Maquet Critical Care Ab Peep regulation for a breathing apparatus
CN102369036A (zh) * 2009-03-27 2012-03-07 马奎特紧急护理公司 呼吸设备的peep调节
US9119925B2 (en) 2009-12-04 2015-09-01 Covidien Lp Quick initiation of respiratory support via a ventilator user interface
US8924878B2 (en) 2009-12-04 2014-12-30 Covidien Lp Display and access to settings on a ventilator graphical user interface
US20110132369A1 (en) * 2009-12-04 2011-06-09 Nellcor Puritan Bennett Llc Ventilation System With System Status Display
US8677996B2 (en) 2009-12-04 2014-03-25 Covidien Lp Ventilation system with system status display including a user interface
US20110132361A1 (en) * 2009-12-04 2011-06-09 Nellcor Puritan Bennett Llc Ventilation System With Removable Primary Display
US20110132362A1 (en) * 2009-12-04 2011-06-09 Nellcor Puritan Bennett Llc Ventilation System With System Status Display Including A User Interface
US8335992B2 (en) 2009-12-04 2012-12-18 Nellcor Puritan Bennett Llc Visual indication of settings changes on a ventilator graphical user interface
US8418692B2 (en) 2009-12-04 2013-04-16 Covidien Lp Ventilation system with removable primary display
US8499252B2 (en) 2009-12-18 2013-07-30 Covidien Lp Display of respiratory data graphs on a ventilator graphical user interface
US9262588B2 (en) 2009-12-18 2016-02-16 Covidien Lp Display of respiratory data graphs on a ventilator graphical user interface
US8443294B2 (en) 2009-12-18 2013-05-14 Covidien Lp Visual indication of alarms on a ventilator graphical user interface
KR101138958B1 (ko) 2010-02-17 2012-04-25 주식회사 멕 아이씨에스 인공 호흡기의 유속 방향 조절 장치
USD656237S1 (en) 2010-04-27 2012-03-20 Nellcor Puritan Bennett Llc Display screen on a system status display
US8539949B2 (en) 2010-04-27 2013-09-24 Covidien Lp Ventilation system with a two-point perspective view
US8511306B2 (en) 2010-04-27 2013-08-20 Covidien Lp Ventilation system with system status display for maintenance and service information
US8453643B2 (en) 2010-04-27 2013-06-04 Covidien Lp Ventilation system with system status display for configuration and program information
USD645158S1 (en) 2010-04-27 2011-09-13 Nellcor Purtian Bennett LLC System status display
US9387297B2 (en) 2010-04-27 2016-07-12 Covidien Lp Ventilation system with a two-point perspective view
US20110284007A1 (en) * 2010-05-21 2011-11-24 Pierre Peron Positive pressure device
US8695591B2 (en) 2010-05-26 2014-04-15 Lloyd Verner Olson Apparatus and method of monitoring and responding to respiratory depression
US20130174846A1 (en) * 2010-06-19 2013-07-11 The Lung Barometry Sweden Ab C/O Stenqvist System and method for determination of transpulmonary pressure in a patient connected to a breathing apparatus
US11154217B2 (en) 2010-06-19 2021-10-26 The Lung Barometry Sweden AB System and method for determination of transpulmonary pressure in a patient connected to a breathing apparatus
US20140296730A1 (en) * 2010-06-19 2014-10-02 M Stenqvist Ab System and Method for Determination of Transpulmonary Pressurein a Patient Connected to a Breathing Apparatus
US9655544B2 (en) * 2010-06-19 2017-05-23 The Lung Barometry Sweden AB System and method for determination of transpulmonary pressure in a patient connected to a breathing apparatus
US8701663B2 (en) * 2010-06-19 2014-04-22 The Lung Barometry Sweden AB System and method for determination of transpulmonary pressure in a patient connected to a breathing apparatus
US9713689B2 (en) 2010-07-12 2017-07-25 Laurent Brochard Methods of evaluating a patient for PEEP therapy
US8695594B2 (en) * 2010-12-06 2014-04-15 General Electric Company System and method of automated lung recruitment maneuvers
US20120138057A1 (en) * 2010-12-06 2012-06-07 General Electric Company System and Method of Automated Lung Recruitment Maneuvers
US20130032149A1 (en) * 2011-08-04 2013-02-07 General Electric Company Method and system for visualizing mechanical ventilation information
US10085674B2 (en) 2011-09-22 2018-10-02 Koninklijke Philips N.V. Method and apparatus for monitoring and controlling a pressure support device
CN103813825A (zh) * 2011-09-22 2014-05-21 皇家飞利浦有限公司 用于监测和控制压力支持设备的方法与装置
US11497869B2 (en) 2011-12-07 2022-11-15 Covidien Lp Methods and systems for adaptive base flow
US9364624B2 (en) 2011-12-07 2016-06-14 Covidien Lp Methods and systems for adaptive base flow
US10543327B2 (en) 2011-12-07 2020-01-28 Covidien Lp Methods and systems for adaptive base flow
US11833297B2 (en) 2011-12-31 2023-12-05 Covidien Lp Methods and systems for adaptive base flow and leak compensation
US10709854B2 (en) 2011-12-31 2020-07-14 Covidien Lp Methods and systems for adaptive base flow and leak compensation
US9498589B2 (en) 2011-12-31 2016-11-22 Covidien Lp Methods and systems for adaptive base flow and leak compensation
US9022031B2 (en) 2012-01-31 2015-05-05 Covidien Lp Using estimated carinal pressure for feedback control of carinal pressure during ventilation
US8844526B2 (en) 2012-03-30 2014-09-30 Covidien Lp Methods and systems for triggering with unknown base flow
US10029057B2 (en) 2012-03-30 2018-07-24 Covidien Lp Methods and systems for triggering with unknown base flow
US10362967B2 (en) 2012-07-09 2019-07-30 Covidien Lp Systems and methods for missed breath detection and indication
US11642042B2 (en) 2012-07-09 2023-05-09 Covidien Lp Systems and methods for missed breath detection and indication
USD741879S1 (en) * 2012-07-30 2015-10-27 General Electric Company Display screen or portion thereof with graphical user interface
USD847830S1 (en) 2012-07-30 2019-05-07 General Electric Company Display screen or portion thereof with graphical user interface
USD797116S1 (en) 2012-07-30 2017-09-12 General Electric Company Display screen or portion thereof with graphical user interface
US9492629B2 (en) 2013-02-14 2016-11-15 Covidien Lp Methods and systems for ventilation with unknown exhalation flow and exhalation pressure
US9981096B2 (en) 2013-03-13 2018-05-29 Covidien Lp Methods and systems for triggering with unknown inspiratory flow
US9808591B2 (en) 2014-08-15 2017-11-07 Covidien Lp Methods and systems for breath delivery synchronization
US10864336B2 (en) 2014-08-15 2020-12-15 Covidien Lp Methods and systems for breath delivery synchronization
US11712174B2 (en) 2014-10-27 2023-08-01 Covidien Lp Ventilation triggering
US9950129B2 (en) 2014-10-27 2018-04-24 Covidien Lp Ventilation triggering using change-point detection
US10940281B2 (en) 2014-10-27 2021-03-09 Covidien Lp Ventilation triggering
US9925346B2 (en) 2015-01-20 2018-03-27 Covidien Lp Systems and methods for ventilation with unknown exhalation flow
CN107405107A (zh) * 2015-03-17 2017-11-28 弗里茨·斯蒂芬医疗技术有限责任公司 呼吸器及其控制方法
USD775345S1 (en) 2015-04-10 2016-12-27 Covidien Lp Ventilator console
US20180140793A1 (en) * 2015-05-25 2018-05-24 The Lung Barometry Sweden AB Method, system and software for protective ventilation
US10881822B2 (en) * 2015-05-25 2021-01-05 The Lung Barometry Sweden AB Method, system and software for protective ventilation
US10905838B2 (en) * 2015-09-03 2021-02-02 Hamilton Medical Ag Ventilator with error detection for flow sensors
US20200038610A1 (en) * 2016-12-20 2020-02-06 Koninklijke Philips N.V. Determining respiratory mechanic parameters in the presence of intrinsic positive end-expiratory pressure
US11883593B2 (en) * 2016-12-20 2024-01-30 Koninklijke Philips N.V. Determining respiratory mechanic parameters in the presence of intrinsic positive end-expiratory pressure
US20190125994A1 (en) * 2017-10-27 2019-05-02 OrangeMed, Inc. Ventilators and systems for performing automated ventilation procedures
CN111712290A (zh) * 2018-02-12 2020-09-25 提姆佩尔医疗有限责任公司 用于确定患者对肺泡复张手法的应答性的系统和方法
US20220096765A1 (en) * 2019-01-29 2022-03-31 Drägerwerk AG & Co. KGaA Ventilation apparatus and ventilation method
US11324954B2 (en) 2019-06-28 2022-05-10 Covidien Lp Achieving smooth breathing by modified bilateral phrenic nerve pacing
US12036409B2 (en) 2019-06-28 2024-07-16 Covidien Lp Achieving smooth breathing by modified bilateral phrenic nerve pacing
US11672934B2 (en) 2020-05-12 2023-06-13 Covidien Lp Remote ventilator adjustment
US12144925B2 (en) 2020-05-12 2024-11-19 Covidien Lp Remote ventilator adjustment
US12257437B2 (en) 2020-09-30 2025-03-25 Covidien Lp Intravenous phrenic nerve stimulation lead

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US20120055476A1 (en) 2012-03-08
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EP1767236B1 (en) 2014-03-05
US8469027B2 (en) 2013-06-25
EP1767236A3 (en) 2009-10-28

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