METHODS FOR PROVIDING EXPIRATORY PRESSURE RELIEF IN POSITIVE AIRWAY PRESSURE THERAPY

• US 20110092841A1
• Filed: 12/06/2010
• Published: 04/21/2011
• Est. Priority Date: 01/07/2004
• Status: Active Grant

• Current Assignee: ResMed Pty Ltd. (ResMed Incorporated)
• Original Assignee: Resmed Limited (ResMed Incorporated)
• Inventors: BASSIN, David John
• Granted Patent: US 8,899,231 B2
• Time in Patent Office: Days
• US Class Current: 600/538
• CPC Class Codes: A61B 5/087 Measuring breath flow
• CPC Class Codes: A61B 5/4818 Sleep apnoea
• CPC Class Codes: A61B 5/725 using specific filters therefor, e.g. Kalman or adaptive filters A61B5/316 take precedence
• CPC Class Codes: A61B 5/7264 Classification of physiological signals or data, e.g. using neural networks, statistical classifiers, expert systems or fuzzy systems neural networks per se G06N3/00; expert systems per se G06N5/00
• CPC Class Codes: A61B 5/7282 Event detection, e.g. detecting unique waveforms indicative of a medical condition A61B5/4094, A61B5/4818, A61B5/349, A61B5/0823 take precedence
• CPC Class Codes: A61M 16/00 Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes stimulating the respiratory movement by mechanical, pneumatic or electrical means, iron lungs combined with gas breathing means A61H31/00
• CPC Class Codes: A61M 16/0003 Accessories therefor, e.g. sensors, vibrators, negative pressure
• CPC Class Codes: A61M 16/0069 the speed thereof being controlled by respiratory parameters, e.g. by inhalation
• CPC Class Codes: A61M 16/024 including calculation means, e.g. using a processor
• CPC Class Codes: A61M 16/06 Respiratory or anaesthetic masks
• CPC Class Codes: A61M 2016/0024 with an on-off output signal, e.g. from a switch
• CPC Class Codes: A61M 2016/0042 in the expiratory circuit

Abstract

A method of operating a CPAP apparatus in which the interface pressure is controlled to rapidly drop at the start of expiration by an expiratory relief pressure (ERP) that is independent of instantaneous respiratory flow, following which the pressure rises to an inspiratory level at or shortly before the end of expiration, or at the onset of an expiratory pause, if any. The ERP is an increasing function of the inspiratory pressure. The expiratory pressure follows a template that is a function of the expected expiration time, the magnitude of the template being equal to the ERP. The current estimated proportion of expiration is determined by comparing the expiration time of the breath in progress to low-pass filtered expiratory durations measured for a number of the preceding breaths.

Claims

1-32. -32. (canceled)

33. A method of determining the expiratory proportion of a breath, p, comprising the steps of:

monitoring a respiratory flow of air of a patient;

calculating an expected duration of expiration, d, from at least one prior breath from said respiratory flow;

determining the start of exhalation of the patient within the breath;

calculating a time, t, since the start of exhalation of the patient; and

calculating p from the ratio of t and d.

34. A method in accordance with claim 33 wherein the expected duration of a breath is calculated by low pass filtering a time series of prior expiratory durations.

35. A method in accordance with claim 34 wherein the low pass filter is an Infinite Impulse Response (IIR) filter.

36. A method in accordance with claim 35 wherein the IIR filter is first-order.

37. A method in accordance with claim 33 wherein the expected expiratory duration, d_m+1, of the (m+1)th breath is calculated from the duration of the current breath d_m, the previous breath d_m−

1 and a constant k in accordance with the following equation;

d_m+1=kd_m+(1−

k)d<sub>m−

1</sub>

38. A method in accordance with claim 34, wherein a low pass filter update T_exp,LPF,m, being the expected expiratory duration to be used for the next breath, is calculated by the following equation:

T_exp,LPF,m=kT_exp,m+(1−

k)T<sub>exp,LPF,m−

1</sub>

where k is a constant, T_exp,m is the expiratory duration measured for the current breath m, and T<sub>exp,LPF,m−

1</sub> is the previous filter update calculated for the preceding breath.

39. A method in accordance with claim 37 wherein the constant k is generally in the range of 0.1 to 0.2.

40. A method in accordance with claim 33 wherein the expected duration of a breath is calculated using a median filter.

41. A method in accordance with claim 40 wherein the median filter has a length in the range of 5 to 7 elements.

54. A method in accordance with claim 35, wherein a low pass filter update T_exp,LPF,m, being the expected expiratory duration to be used for the next breath, is calculated by the following equation:

T_exp,LPF,m=kT_exp,m+(1−

k)T<sub>exp,LPF,m−

1</sub>

where k is a constant, T_exp,m is the expiratory duration measured for the current breath m, and T<sub>exp,LPF,m−

1</sub> is the previous filter update calculated for the preceding breath.

55. A method in accordance with claim 38 wherein the constant k is generally in the range of 0.1 to 0.2.

42. A method of detecting an expiratory pause in a breath comprising the steps of:

continuously calculating a flow signal indicative of a respiratory flow of air to a patient;

determining whether the flow signal is an expiratory flow signal;

determining that an expiratory pause has commenced when expiratory flow signal exceeds a small negative threshold;

43. A method as claimed in claim 42 wherein the flow signal is filtered

44. A method as claimed in claim 43 wherein the filter is a low pass filter with a low −

3 dB point of approximately 5 Hz.

45. A method as claimed in claim 42 wherein the small negative threshold is about −

0.07 I/sec.

46. A method as claimed in claim 43 wherein the filter is a time-symmetrical Finite Impulse Response (FIR) filter.

47. A method of determining the duration of an expiratory pause comprising the step of determining the duration of the longest contiguous period ending at the end of expiration such that the respiratory flow during that period does not lie outside a range of values which represents small flow.

48. A method as claimed in claim 47 wherein the range of values is generally from −

0.7 I/sec to +0.7 I/sec.

49. A method of determining the expiratory pause fraction of a breath, k, comprising the steps of:

continuously calculating a flow signal indicative of a respiratory flow of air to a patient;

calculating a rate of change of said flow signal;

determining a fuzzy extent to which the flow signal is indicative of an expiratory pause from said flow and rate;

calculating a value F from low pass filtering said fuzzy extent; and

calculating the expiratory pause fraction, k, from the equation;

k=1−

F.

50. A method as claimed claim 49 wherein the fuzzy extent to which the flow signal is indicative of an expiratory pause is calculated in accordance with the fuzzy rule that if the flow signal is zero and the rate of change of the flow signal is steady then the fuzzy phase is expiratory pause.

51. A method as claimed in claim 49 wherein the low pass filter has the property that it is only updated during expiration.

52. A method as claimed in claim 49 wherein the low pass filter is a first order low pass filter.

53. A method as claimed in claim 49 wherein the low pass filter has a time constant of approximately four times the long-term average of the respiratory period.