Method and apparatus for precision monitoring of infants on assisted ventilation

• US 4,972,842 A
• Filed: 06/09/1988
• Issued: 11/27/1990
• Est. Priority Date: 06/09/1988
• Status: Expired due to Fees

• Current Assignee: Vital Signs Incorporated (Becton, Dickinson & Co)
• Original Assignee: Vital Signs Incorporated (Becton, Dickinson & Co)
• Inventors: Schulze, Karl F., Korten, Jerome B.
• Primary Examiner(s): Cohen, Lee S.
• Application Number:
  US07/204,460
• Time in Patent Office: 901 Days
• Field of Search: 128/716, 128/720, 128/725, 128/200.24, 128/204.23, 128/202.22, 600/22
• US Class Current: 600/529
• CPC Class Codes: A61B 5/087 Measuring breath flow
• CPC Class Codes: A61B 5/7239 using differentiation including higher order derivatives
• CPC Class Codes: G16H 20/40 relating to mechanical, radiation or invasive therapies, e.g. surgery, laser therapy, dialysis or acupuncture
• CPC Class Codes: G16H 40/63 for local operation
• CPC Class Codes: G16Z 99/00 Subject matter not provided for in other main groups of this subclass

Abstract

An apparatus and method are disclosed for monitoring physiological parameters associated with the ventilation of infants during assisted ventilation. The infant is placed in a plethysmograph and various sensor means are used to measure flow of gas into and out of the plethysmograph and infant respiration. The outputs of the sensor means are supplied to a microcomputer system for processing. A unique calibration system is provided which constantly corrects for changing system parameters such as plethysmographic chamber air leaks, compliance and the like. Additionally, a heating system which exhibits radiant as well as convective heating properties is provided to maintain the infant in a constant temperature environment with a minimal amount of temperature fluctuation. From this data, ventilator breaths are discriminated from infant breaths.

Claims

1. An apparatus for obtaining continuous measurements of infant ventilation during assisted ventilation by an assisted ventilation gas source comprising:

a plethysmograph having at least an input port,

means for coupling an assisted ventilation gas source to said input port of said plethysmograph,

a pressure pulse source coupled to said plethysmograph for applying a pressure pulse of known volume into said plethysmograph,

an endotracheal tube having a first end which is coupled to said input port and a second end which is insertable into an airway of an infant placed in said plethysmograph such that said airway is isolated from the interior of said plethysmograph,

a pneumotachometer attached to said plethysmograph and having a resistance to air flow and being adapted for providing a pressure differential on opposite sides of said pneumotachometer,

a differential pressure transducer coupled to said pneumotachometer for outputting a differential pressure signal reflecting said pressure differential, said differential pressure signal being proportional to a flow signal indicating a flow rate through said pneumotachometer,

means for detecting pressure changes in said endotracheal tube caused by said assisted ventilation gas source and breathing efforts of said infant and for outputting an airway pressure signal in accordance with such pressure changes,

means for converting said differential pressure signal into digital data,

a preprogrammed computer system having;

means for calculating digitized flow data from said digitized differential pressure data,

means for frequency correcting said digitized flow data,

means for determining from said frequency corrected digitized data at least whether pressure changes in the interior of said plethysmograph are due to assisted ventilation or to the infant'"'"'s breathing efforts and for determining a resultant volumetric displacement from said frequency corrected digitized flow data.

2. The apparatus of claim 1 further comprising means for gain correcting said digitized flow data.

3. The apparatus of claim 2 wherein said gain correcting means comprises means for integrating said digitized flow data and comparing said integrated flow data with a known volume displaced by activation of said pressure pulse source.

4. The apparatus of claim 3 wherein said pressure pulse source comprises a linear displacement actuator.

5. The apparatus of claim 1 further comprising a radiant heater located external to said plethysmograph and which radiates heat energy towards said plethysmograph and said infant and which produces convective heating within said plethysmograph.

6. The apparatus of claim 1 wherein said frequency correcting means comprises means for calculating a time constant of said plethysmograph and multiplying said time constant by a first derivative of said flow data with respect to time and adding the result to said flow data to provide frequency corrected flow data.

7. The apparatus of claim 6 wherein said time constant is the resistance of air flow openings in said plethysmograph multiplied by the compliance of air inside the plethysmograph.

8. The apparatus of claim 1 wherein said means for detecting pressure changes caused by said ventilation source comprises a pressure transducer adapted for sensing pressure in said endotracheal tube.

9. The apparatus of claim 8 wherein said pneumotachometer is positioned in an opening through a wall of said plethysmograph.

10. The apparatus of claim 1 wherein said means for detecting pressure changes caused by said ventilation source comprises:

a second pneumotachometer coupled to an exhaust port of said ventilator, and

a pressure transducer coupled to said second pneumotachometer.

11. The apparatus of claim 1 wherein said plethysmograph comprises a first section having a tapered edge and a second section hinged to said first section and sealable with said first section by way of a gasketing material placed on an edge of said second section for sealing contact with said tapered edge.

12. The apparatus of claim 11 further comprising means for moving said first section directly away from said second section to provide uniform sealing pressure between said tapered edge and said gasketing material.

13. The apparatus of claim 1 further comprising means for calculating systolic blood pressure and diastolic blood pressure of the infant.

14. The apparatus of claim 13 wherein said calculating means calculates a systolic pressure value by determining a maximum amplitude of a blood pressure waveform between a positive threshold value of a first derivative of said blood pressure waveform and a negative threshold value of said first derivative of said blood pressure waveform, said maximum amplitude being the diastolic pressure.

15. The apparatus of claim 14 wherein said calculating means calculates diastolic pressure by determining a local minimum of the blood pressure waveform between said systolic pressure value and a previous systolic pressure value, said local minimum being the diastolic pressure.

16. The apparatus of claim 1 further comprising means for synchronizing said infant'"'"'s breath with said assisted ventilation.

17. A method for precisely calculating a flow rate of air into and out of a plethysmograph occasioned by breathing efforts of an infant and ventilatory assistance comprising:

measuring a difference in pressure across a pneumotachometer due to a flow rate into and out of said plethysmograph by a differential pressure transducer,

frequency correcting a signal output by said differential pressure transducer, said signal being proportional to said flow rate and said difference in pressure,

gain correcting the signal output by said differential pressure transducer,

wherein said frequency correcting and said gain correcting of said signal provides a gain and frequency corrected signal which precisely and accurately represents the flow of gas into and out of said infant'"'"'s lungs.

18. The method of claim 17 wherein said frequency correcting comprises calculating a time constant of said plethysmograph and multiplying said time constant by a first derivative of said signal with respect to time and adding the result to said signal to provide a frequency corrected signal.

19. The method of claim 18 wherein said time constant is the resistance of air flow openings in said plethysmograph multiplied by the compliance of air inside the plethysmograph.

20. The method of claim 17 wherein said gain correcting comprises integrating said signal output by said differential pressure transducer and comparing said integrated signal with a known volume displaced by activation of a pressure pulse source coupled to said plethysmograph.

21. An improved plethysmograph of the type having a substantially enclosed plethysmographic chamber for receiving an infant, an assisted ventilation gas source coupled to said chamber, an endotracheal tube insertable into an airway of said infant, and means attached to said plethysmographic chamber for measuring airflow into and out of said plethysmographic chamber, wherein the improvement comprises a radiant heater external to said plethysmographic chamber which radiates heat towards said plethysmographic chamber thereby raising the temperature of said infant'"'"'s skin and which also convectively heats said infant by heating air contained within said plethysmographic chamber, thereby accurately and precisely maintaining a desired temperature of said infant'"'"'s skin.

22. An improved plethysmograph of the type having a substantially enclosed plethysmographic chamber for receiving an infant, an assisted ventilation gas source coupled to said chamber, an endotracheal tube insertable into an airway of said infant, and means attached to said plethysmographic chamber for measuring airflow into and out of said plethysmographic chamber, wherein the improvement comprises a linear displacement actuator coupled to said plethysmographic chamber for applying a pressure pulse of known volume into said plethysmograph.

23. An improved method of operating a plethysmograph of the type having a substantially enclosed plethysmographic chamber for receiving an infant, an assisted ventilation gas source coupled to said chamber, an endotracheal tube insertable into an airway of said infant, a pneumotachometer and a differential pressure transducer attached to said plethysmographic chamber, said transducer outputting a flow signal indicating a flow rate through said pneumotachometer, wherein the improvement comprises frequency correcting and gain correcting the flow signal output by said differential pressure transducer.

24. The improved method of claim 23 wherein said frequency correcting comprises calculating a time constant of said plethysmograph and multiplying said time constant by a first derivative of said flow signal with respect to time and adding the result to said flow signal to provide a frequency corrected flow signal.

25. The improved method of claim 24 wherein said time constant is the resistance of air flow openings in said plethysmograph multiplied by the compliance of air inside the plethysmograph.

26. The improved method of claim 25 wherein said gain correcting comprises integrating said flow signal output by said differential pressure transducer and comparing said integrated flow signal with a known volume displaced by activation of a pressure pulse source.

27. The improved method of claim 26 wherein said pressure pulse source displaces a known volume into and out of said plethysmograph.

28. An apparatus for obtaining continuous measurements of infant ventilation during assisted ventilation by an assisted ventilation gas source comprising:

a plethysmograph having at least an input port,

means for coupling an assisted ventilation gas source to said input port of said plethysmograph,

a pressure pulse source coupled to said plethysmograph for applying a pressure pulse of known volume into said plethysmograph,

an endotracheal tube having a first end which is coupled to said input port and a second end which is insertable into an airway of an infant placed in said plethysmograph such that said airway is isolated from the interior of said plethysmograph,

means for outputting a flow signal indicating a flow rate into and out of said plethysmograph,

means for detecting pressure changes in said endotracheal tube caused by said assisted ventilation gas source and breathing efforts of said infant and for outputting an airway pressure signal in accordance with such pressure changes,

means for converting said flow signal into a digital flow signal,

a preprogrammed computer system having;

means for calculating digitized flow data from said digitized flow signal,

means for frequency correcting said digitized flow data,

means for determining from said frequency corrected digitized data at least whether pressure changes in the interior of said plethysmograph are due to assisted ventilation or to the infant'"'"'s breathing efforts and for determining a resultant volumetric displacement from said frequency corrected digitized flow data.

29. The apparatus of claim 28 wherein said means for outputting said flow signal comprises means adapted for creating a pressure differential between the interior of said plethysmograph and the exterior of said plethysmograph, and transducer means for outputting said flow signal which indicates a magnitude of said pressure differential.

30. The apparatus of claim 28 wherein said means for outputting said flow signal comprises:

a pneumotachometer attached to said plethysmograph and having a resistance to air flow and being adapted for providing a pressure differential on opposite sides of said pneumotachometer, and

a differential pressure transducer coupled to said pneumotachometer for outputting a differential pressure signal reflecting said pressure differential, said differential pressure signal being proportional to a flow signal indicating a flow rate through said pneumotachometer.

31. The apparatus of claim 28 further comprising means for gain correcting said digitized flow data.

32. The apparatus of claim 31 wherein said gain correcting means comprises means for integrating said digitized flow data and comparing said integrated flow data with a known volume displaced by activation of said pressure pulse source.

33. The apparatus of claim 28 further comprising a radiant heater located external to said plethysmograph and which radiates heat energy towards said plethysmograph and said infant and which produces convective heating within said plethysmograph.

34. The apparatus of claim 28 wherein said frequency correcting means comprises means for calculating a time constant of said plethysmograph and multiplying said time constant by a first derivative of said flow data with respect to time and adding the result to said flow data to provide frequency corrected flow data.

35. The apparatus of claim 34 wherein said time constant is the resistance of air flow openings in said plethysmograph multiplied by the compliance of air inside the plethysmograph.

36. The apparatus of claim 28 further comprising means for calculating systolic blood pressure and diastolic blood pressure of the infant.

37. The apparatus of claim 36 wherein said calculating means calculates a systolic pressure value by determining a maximum amplitude of a blood pressure waveform between a positive threshold value of a first derivative of said blood pressure waveform and a negative threshold value of said first derivative of said blood pressure waveform, said maximum amplitude being the diastolic pressure.

38. The apparatus of claim 37 wherein said calculating means calculates diastolic pressure by determining a local minimum of the blood pressure waveform between said systolic pressure value and a previous systolic pressure value, said local minimum being the diastolic pressure.

39. The apparatus of claim 28 further comprising means for synchronizing said infant'"'"'s breath with said assisted ventilation.

40. An improved method of operating a plethysmograph of the type having a substantially enclosed plethysmographic chamber for receiving an infant, an assisted ventilation gas source coupled to said chamber, an endotracheal tube insertable into an airway of said infant, and means for producing a flow signal which indicates air flow into and out of said chamber, wherein the improvement comprises the steps of frequency correcting and gain correcting said flow signal output by said flow signal producing means.

41. The improved method of claim 40 wherein said frequency correcting step comprises calculating a time constant of said plethysmograph and multiplying said time constant by a first derivative of said flow signal with respect to time and adding the result to said flow signal to provide a frequency corrected flow signal.

42. The improved method of claim 41 wherein said time constant is the resistance of air flow openings in said plethysmograph multiplied by the compliance of air inside the plethysmograph.

43. The improved method of claim 42 wherein said gain correcting step comprises integrating said flow signal and comparing said integrated flow signal with a known volume displaced by activation of a pressure pulse source.

44. The improved method of claim 48 wherein said pressure pulse source displaces a known volume into and out of said plethysmograph.