U.S. patent application number 15/484725 was filed with the patent office on 2017-08-03 for methods and apparatus for pressure therapy in the treatment of sleep disordered breathing.
This patent application is currently assigned to ResMed Limited. The applicant listed for this patent is ResMed Limited. Invention is credited to Adrian Barnes, Christopher Kingsley Blunsden, John David Oates, Chinmayee Somaiya, Nicholas Ming Yun Yip.
Application Number | 20170216542 15/484725 |
Document ID | / |
Family ID | 39892258 |
Filed Date | 2017-08-03 |
United States Patent
Application |
20170216542 |
Kind Code |
A1 |
Somaiya; Chinmayee ; et
al. |
August 3, 2017 |
METHODS AND APPARATUS FOR PRESSURE THERAPY IN THE TREATMENT OF
SLEEP DISORDERED BREATHING
Abstract
A controller or processor for a respiratory pressure treatment
device determines an estimate of patient respiratory flow based on
a measure of pressure associated with flow generated by a flow
generator and a measure of frequency of the flow generator, such as
a rotational velocity of a servo-controlled blower motor. The
estimate can be made without data from a flow sensor. The measure
of frequency may be converted to an expected pressure based on
characteristics of the flow generator and subtracted from the
measured pressure to determine the flow estimate. The flow estimate
can be implemented in the provision of respiratory pressure
treatment with the flow generator. For example, the flow estimate
may be utilized to trigger expiratory pressure relief during a
patient's expiration as detected with the estimated flow
signal.
Inventors: |
Somaiya; Chinmayee; (Sydney,
AU) ; Yip; Nicholas Ming Yun; (Kings Langley, AU)
; Oates; John David; (Castle Hill, AU) ; Barnes;
Adrian; (Cammeray, AU) ; Blunsden; Christopher
Kingsley; (Newport Beach, AU) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
ResMed Limited |
Bella Vista |
|
AU |
|
|
Assignee: |
ResMed Limited
Bella Vista
AU
|
Family ID: |
39892258 |
Appl. No.: |
15/484725 |
Filed: |
April 11, 2017 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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12192247 |
Aug 15, 2008 |
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15484725 |
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61125066 |
Apr 22, 2008 |
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60965171 |
Aug 17, 2007 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61B 5/4818 20130101;
A61M 16/06 20130101; A61M 2205/52 20130101; A61M 2205/3365
20130101; A61B 5/4836 20130101; A61M 2016/0027 20130101; A61M
2205/3331 20130101; A61M 16/0066 20130101; A61B 5/087 20130101;
A61M 16/026 20170801; A61M 16/0069 20140204; A61M 16/0051
20130101 |
International
Class: |
A61M 16/00 20060101
A61M016/00; A61M 16/06 20060101 A61M016/06 |
Claims
1-34. (canceled)
35. A method of controlling pressure in a pressure treatment
delivery apparatus to compensate for patient induced swing at a
patient interface, the method comprising: determining a measure of
pressure delivered by a flow generator with a pressure sensor, the
pressure sensor being located proximate to the flow generator;
adjusting the measure of pressure as a function of (a) a measure of
pressure drop across the flow generator, (b) a measure of impedance
of a patient interface coupled to the flow generator and (c) a
measure of impedance of the flow generator; and controlling the
flow generator so that the adjusted measure of pressure satisfies a
target pressure setting.
36. The method of claim 35 wherein the function multiplies the
measure of pressure drop with a ratio of the measure of impedance
of the patient interface and the measure of impedance of the flow
generator.
37. The method of claim 36 wherein a result of the function is
subtracted from the measure of pressure.
38. The method of claim 37 wherein the measure of pressure drop is
a difference between a measure of pressure and a derived measure of
pressure that is a determined function of a frequency of the flow
generator.
39. A pressure treatment delivery apparatus to compensate for
patient induced swing comprising: a patient interface to carry a
flow of breathable gas to a patient; a flow generator coupled with
the patient interface to generate a flow of the breathable gas
through the patient interface; a pressure sensor to provide a
pressure signal indicative of pressure associated with the flow
generator; and a processor to control the flow generator, the
processor coupled with the pressure sensor to process the pressure
signal, the processor being configured to control: determining a
measure of pressure delivered by a flow generator with the pressure
sensor, the pressure sensor being located proximate to the flow
generator; adjusting the measure of pressure as a function of (a) a
measure of pressure drop across the flow generator, (b) a measure
of impedance of a patient interface and (c) a measure of impedance
of the flow generator; and controlling the flow generator so that
the adjusted measure of pressure satisfies a target pressure
setting.
40. The apparatus of claim 39 wherein the function multiplies the
measure of pressure drop with a ratio of the measure of impedance
of the patient interface and the measure of impedance of the flow
generator.
41. The apparatus of claim 40 wherein a result of the function is
subtracted from the measure of pressure.
42. The apparatus of claim 41 wherein the measure of pressure drop
is a difference between a measure of pressure and a derived measure
of pressure that is a determined function of a frequency of the
flow generator.
43. A pressure treatment delivery system to compensate for patient
induced swing comprising: a patient interface means for carrying a
flow of breathable gas to a patient; a flow generation means
coupled with the patient interface for generating a flow of the
breathable gas through the patient interface; a sensor means for
providing a pressure signal indicative of pressure associated with
the flow generator; and a control means, coupled with the sensor
means and flow generation means, for determining a measure of
pressure delivered by the flow generation means, for adjusting the
measure of pressure as a function of (a) a measure of pressure drop
across the flow generator, (b) a measure of impedance of a patient
interface and (c) a measure of impedance of the flow generator, and
for controlling the flow generator so that the adjusted measure of
pressure satisfies a target pressure setting.
44. The system of claim 43 wherein the function multiples the
measure of pressure drop with a ratio of the measure of impedance
of the patient interface and the measure of impedance of the flow
generator.
45. The system of claim 44 wherein a result of the function is
subtracted from the measure of pressure.
46. The system of claim 45 wherein the measure of pressure drop is
a difference between a measure of pressure and a derived measure of
pressure that is a determined function of a frequency of the flow
generator.
47. An information-bearing medium having processor-readable
information thereon, the processor-readable information to control
an apparatus for providing pressure treatment therapy to compensate
for patient induced swing, the processor-readable information
comprising control instructions to: determine a measure of pressure
delivered by a flow generator with a pressure sensor that is
located proximate to the flow generator; adjust the measure of
pressure as a function of (a) a measure of pressure drop across the
flow generator, (b) a measure of impedance of a patient interface
coupled to the flow generator and (c) a measure of impedance of the
flow generator; and control the flow generator so that the adjusted
measure of pressure satisfies a target pressure setting.
48. The medium of claim 47 wherein the function multiplies the
measure of pressure drop with a ratio of the measure of impedance
of the patient interface and the measure of impedance of the flow
generator.
49. The medium of claim 48 wherein a result of the function is
subtracted from the measure of pressure.
50. The medium of claim 47 wherein the measure of pressure drop is
a difference between a measure of pressure and a derived measure of
pressure that is a determined function of a frequency of the flow
generator.
Description
CROSS REFERENCE TO RELATED APPLICATIONS
[0001] This application claims the benefit of the filing dates of
U.S. Provisional Patent Application Nos. 60/965,171 filed Aug. 17,
2007 and 61/125,066 filed Apr. 22, 2008, the disclosures of which
are hereby incorporated herein by reference.
FIELD OF THE TECHNOLOGY
[0002] The present technology relates to methods and apparatus for
treatment of respiratory conditions such as the conditions related
to obstructive sleep apnea hypopnea syndrome (OSAHS) or obstructive
sleep apnea (OSA).
BACKGROUND OF THE TECHNOLOGY
[0003] Patients with OSA have recurrent apnoeas or hypopnoeas
during sleep that are only terminated by the patient arousing.
These recurrent events cause sleep fragmentation and stimulation of
the sympathetic nervous system. This can have severe consequences
for the patient including day-time sleepiness (with the attendant
possibility of motor-vehicle accidents), poor mentation, memory
problems, depression and hypertension. Patients with OSA are also
likely to snore loudly, thus also disturbing their partner's sleep.
The best form of treatment for patients with OSA is constant
positive airway pressure (CPAP) applied by a blower (compressor)
via a connecting hose and mask (patient interface). The positive
pressure prevents collapse of the patient's airway during
inspiration, thus preventing recurrent apnoeas or hypopnoeas and
their sequelae.
[0004] Positive airway pressure may be delivered in many forms. For
example, a positive pressure level may be maintained across the
inspiratory and expiratory levels of the patient's breathing cycle
at an approximately constant level. Alternatively, pressure levels
may be adjusted to change synchronously with the patient's
breathing cycle. For example, pressure may be set at one level
during inspiration and another lower level during expiration for
patient comfort. Such a pressure treatment system may be referred
to as bi-level. Alternatively, the pressure levels may be
continuously adjusted to smoothly replicate changes in the
patient's breathing cycle. A lower pressure setting during
expiration may generally be referred to as expiratory pressure
relief.
[0005] In providing such changes to pressure and/or detecting
conditions for making adjustments to the treatment pressure, it can
be helpful to have a measure of patient respiratory flow. For
example, a measure of patient respiratory flow may be utilized to
detect when a patient changes from inspiration to expiration for
determining when to deliver expiratory pressure treatment settings
or inspiratory pressure treatment settings. Similarly, a measured
patient respiratory flow signal may be utilized to detect patient
flow limitation for purposes of making treatment pressure
adjustments. Such adjustments are illustrated in the patent in U.S.
Pat. No. 5,704,345. For these purposes, a measured flow signal may
be derived from a flow sensor such as a differential pressure
transducer or pnuemotachograph.
[0006] It may be desirable to develop further methods and devices
for estimating flow to improve existing methods and devices and/or
to develop new pressure treatment and detection methods and
devices.
SUMMARY OF THE TECHNOLOGY
[0007] Aspects of the present technology involve methods for a
respiratory flow generating apparatus. In one method, a measure of
pressure produced by a respiratory flow generating apparatus and a
measure of a frequency of the respiratory flow generating apparatus
are determined. The method then derives an estimate of patient
respiratory flow as a function of the measure of pressure and the
measure of frequency. In some embodiments, the measure of frequency
may be a rotational velocity. Moreover, the deriving of the
estimate may further include determining an expected pressure as a
function of the measure of frequency and may further include
calculating a difference between the determined expected pressure
and the measure of pressure. Pressure treatment by the respiratory
flow generating apparatus may be set or adjusted as a function of
the derived estimate of respiratory flow.
[0008] In one embodiment, the technology encompasses an apparatus
for generating respiratory flow. The apparatus may optionally
include a patient interface to carry a flow of breathable gas to a
patient. The apparatus may further include a flow generator coupled
with the patient interface to generate a flow of the breathable gas
through the patient interface. The apparatus may also include
measurement sensors such as a pressure transducer to provide a
pressure signal indicative of pressure in a portion of the patient
interface or associated with the flow generator and a tachometer to
provide a velocity signal indicative of a speed of the flow
generator. The apparatus may also be provided with a controller to
control the flow generator. The controller is coupled with the
pressure transducer to process the pressure signal and it is
coupled with the tachometer to process the velocity signal. The
controller may be configured and adapted to control a method for
estimating patient respiratory flow or to set delivered treatment
pressure by a method as described herein such as by determining a
measure of pressure with the pressure signal, determining a measure
of frequency with the velocity signal and deriving an estimate of
patient respiratory flow as a function of the measure of pressure
and the measure of frequency.
[0009] In a further embodiment, a system for delivering respiratory
flow to a patient includes an interface means to carry a flow of
breathable gas. The system may also include a flow means, coupled
with the interface means, for generating the breathable gas. The
system may have a pressure sensing means for measuring pressure and
for generating a pressure signal representing the measured pressure
of the breathable gas as well as a frequency sensing means for
measuring a frequency of the flow means and for generating a
frequency signal representing the measured frequency. The system
will typically also include a processing means for processing the
pressure signal and the frequency signal. The processing means may
be configured or adapted for processing a determination of a
measure of pressure with the pressure signal, a determination of a
measure of frequency with the frequency signal and a derivation of
an estimate of patient respiratory flow as a function of the
measure of pressure and the measure of frequency. The processing
means may also be configured for controlling a generation of
pressure with the flow means as a function of the derived estimate
of respiratory flow. In an embodiment of the system, changes to
pressure treatment may be delivered in synchrony with a patient's
respiratory cycle without a flow sensor or utilizing a signal from
a flow sensor.
[0010] In another embodiment, methodology of the technology may be
encoded on an information-bearing medium as software or firmware.
For example, an information-bearing medium may include
processor-readable information or processor control instructions.
The processor-readable information may control an apparatus for
providing pressure treatment therapy. The processor-readable
information or processor control instructions may include steps
that implement determining a measure of pressure produced by a flow
generator, determining a measure of frequency of the flow generator
and deriving an estimate of patient respiratory flow as a function
of the measure of pressure and the measure of frequency.
[0011] Further embodiments and features of the technology will be
apparent from the following detailed disclosure, claims and
drawings.
BRIEF DESCRIPTION OF DRAWINGS
[0012] The present technology is illustrated by way of example, and
not by way of limitation, in the figures of the accompanying
drawings, in which like reference numerals refer to similar
elements including:
[0013] FIG. 1 shows example components of an apparatus for
respiratory flow estimation and pressure treatment based
thereon;
[0014] FIG. 2 is a flow chart for a method for a pressure treatment
or flow estimation apparatus of the present technology;
[0015] FIG. 3 is an illustrative input/output diagram for a control
circuit or processor implementing flow estimation technology;
[0016] FIG. 4 is a graph of an exemplary pressure treatment
waveform implemented by a pressure treatment apparatus utilizing
the present flow estimation technology;
[0017] FIG. 5 is a diagram illustrating suitable components of a
feedback control loop of a pressure treatment device utilizing flow
estimation technology for mask swing adjustment.
DETAILED DESCRIPTION
[0018] In reference to FIG. 1, the present technology may be
implemented with a pressure treatment delivery device that may
include a flow generator such as a servo-controlled blower 102. The
blower 102 will typically include an air inlet and impeller driven
by a motor (not shown).
[0019] In the embodiment illustrated in FIG. 1, a frequency sensor
104 is provided. The sensor may be configured to measure the
rotational velocity of the blower. For example, a tachometer may
measure the revolutions per minute (RPM) of the blower's motor or
the blower's impeller. The frequency sensor 104 may be configured
to generate a frequency signal f(t) indicative of the measurements
of the sensor.
[0020] The device of FIG. 1 may further include a pressure sensor
106, such as a pressure transducer. The pressure sensor 106 is
configured to measure the pressure generated by the blower 102. In
this embodiment, the pressure sensor 106 is proximate to the blower
102 but may be located downstream of the blower as desired. The
pressure sensor 106 generates a pressure signal p(t) indicative of
the measurements of pressure. The pressure sensor 106 and frequency
sensor 104 have only been shown symbolically in FIG. 1 since it is
understood that other configurations and other components may be
implemented to measure the frequency and pressure associated with
the blower 102.
[0021] The pressure treatment delivery device will also typically
include a patient interface such as an air delivery conduit 108 and
a mask 110 to carry a flow of air or breathable gas to and/or from
a patient. The blower 102 can be coupled with the air delivery
conduit 108 and the mask 110 so as to provide the breathable gas
from the blower 102. Exhaust gas can be vented from the patient
interface via an exhaust 111.
[0022] The frequency f(t) and pressure p(t) signals may be sent to
a controller or processor 112. Optional analog-to-digital (A/D)
converters/samplers (not shown separately) may be utilized in the
event that supplied signals from the frequency and pressure sensors
are not in digital form and the controller is a digital controller.
Based on input signals from these sensors and/or other optional
sensors, the controller may in turn generate blower control
signals. For example, the controller may generate an RPM request
signal to control the speed of the blower 102 by setting a desired
frequency or rotational velocity set point and comparing it with
the measured condition of the frequency sensor. Alternatively, such
changes may be based on determining a desired pressure set point
and comparing it with the measured condition of the pressure
sensor. Typically, such changes to the motor speed are accomplished
by increasing or decreasing supplied motor current with the servo
based on determined differences between set and measured conditions
such as in a closed loop feedback fashion and translating the
difference to current. Thus, the processor 112 or controller may
make controlled changes to the pressure delivered to the patient
interface by the blower 102. Optionally, such changes to pressure
may be implemented by controlling the exhaust with a mechanical
release valve (not shown) to increase or decrease the exhaust while
maintaining a relatively constant blower speed.
[0023] The controller or processor 112 is typically configured and
adapted to implement particular control methodology such as the
methods described in more detail herein. Thus, the controller may
include integrated chips, a memory and/or other control
instruction, data or information storage medium. For example,
programmed instructions encompassing such a control methodology may
be coded on integrated chips in the memory of the device or such
instructions may be loaded as software or firmware using an
appropriate medium. With such a controller or processor, the
apparatus can be used for many different pressure treatment
therapies, such as the pressure treatments previously mentioned, by
adjusting a pressure delivery equation that is used to set the
speed or pressure of the blower or the exhaust venting by the
release valve.
[0024] For example, based on such a configuration, an embodiment of
the system may determine or estimate a patient respiratory flow,
even without a flow signal from a flow sensor, and then adjust the
pressure treatment delivered by the device based on patient
respiratory conditions detected from or with the estimated flow
signal. While the flow characteristics of the hose to the mask may
also impact pressure determinations, such a flow estimation model
can be based on the premise that in an rpm-controlled system the
load perturbations (i.e., patient respiratory flow) are reflected
in the pressure output of the device. Similarly, in a
pressure-controlled system the load perturbations will be reflected
in the rpm output of the device.
[0025] Thus, in one embodiment, two measures, such as pressure and
flow generator system frequency (e.g., a rotational velocity of the
blower such as RPM) taken together can give a measure of flow. In
one suitable patient flow estimate, the measured pressure and an
expected pressure value derived from the frequency measure may both
be utilized to derive the flow as a function thereof. This can be
illustrated with the following function:
Flow=function (P.sub.M-P.sub.RPM.sub._.sub.derived)
[0026] Where: [0027] P.sub.M is a measured pressure; [0028]
P.sub.RPM.sub._.sub.derived is an expected pressure at a particular
flow that is determined or calculated from a measured system
variable other than pressure such as frequency or rotational
velocity (e.g., RPM) of the blower. Depending on the flow generator
characteristics and required accuracy, it can also be either a
fixed value or calibrated value.
[0029] In one embodiment, P.sub.RPM.sub._.sub.derived may be
determined or calculated by a static fan curve as follows:
P.sub.RPM-derived=K.sub.2*.omega..sup.2+K.sub.1+K.sub.0
[0030] Where: [0031] .omega. is an angular frequency of the flow
generator (which may also be referred to as angular speed, radial
frequency, and radian frequency); and [0032] K.sub.2, K.sub.1 and
K.sub.0 may be experimentally pre-determined constants for relating
an experimental measure of delivered pressure to a blower's
measured angular frequency based on the particular structural
characteristics of the flow generator or blower (e.g., impeller
design). Optionally, in the case of small constants, the constants
may be uniformly scaled up to reduce operational overhead of
decimal point operations on a device's processor or controller.
[0033] In one embodiment, the flow may then be determined as a
function of the difference between P.sub.M and
P.sub.RPM.sub._.sub.derived by utilizing the following
equation:
Flow=A.sub.3*x.sup.3A.sub.2* x.sup.2+A.sub.1*x+A.sub.0
[0034] Where: [0035] x is P.sub.M minus P.sub.RPM-derived as
previously described; and [0036] A.sub.3, A.sub.2, A.sub.1 and
A.sub.0 may be experimentally pre-determined constants for relating
an experimental measure of flow to a function of the blower's
measured angular frequency and measured pressure based on the
particular structural characteristics of the system.
[0037] However, given the limitations of 32-bit processing, it was
found that the computational complexity was quite high for arriving
at the desired level of performance of flow linearization using the
above equation. Thus, in another embodiment of the technology, in
order to simplify the determination, a look up table may be
pre-formed based on the above equations. A suitable table may be
pre-calculated based on a range of input measures of frequency and
a range of input measures of pressure using the formulas. The
output of the table would then be a derived instantaneous flow
value based on an input instantaneous measure of pressure and an
input instantaneous measure of frequency as previously
described.
[0038] In a still further embodiment of the technology, the derived
flow values may be determined from the difference between the
measured pressure and the frequency derived pressure (e.g.,
P.sub.M--P.sub.RPM.sub._.sub.derived). Thus, the flow may be more
simply estimated by the following equation:
Flow=P.sub.M-P.sub.RPM.sub._.sub.derived
[0039] Where: [0040] P.sub.M is a measured pressure; and [0041]
P.sub.RPM.sub._.sub.derived is an expected pressure that is
determined or calculated from a measured system variable other than
pressure such as frequency or rotational velocity (e.g., RPM or
.omega.) of the blower by any method previously discussed.
[0042] Although this particular estimate is not linearized, it can
give an estimate of flow excursion. Therefore, it is quite suitable
for algorithms that are dependent on cycle detection. In the
absence of further processing, it may not alone be highly suitable
for algorithms that require more accurate flow value or more
accurate flow shape. However, its simplicity can make it
particularly suitable for implementation either as a hardware
component to reduce a system processor load or as firmware/software
for a system processor.
[0043] In a system that employs a continuous system exhaust flow or
leak with which the patient respiratory flow is combined, the above
determined flow values may be further processed to separate the
system or leak flow from the patient respiratory flow by a suitable
operation such as one illustrated by the following equation:
Respiratory Flow=FLW-LPF(FLW)
[0044] Where: [0045] FLW is continuously or periodically determined
flow values derived from any of the previously described methods;
and [0046] LPF(FLW) is a low pass filtering operation on the flow
values with the filtering operation being chosen to remove a
constant component of the flow that can be associated with a
relatively constant leak or system flow. An example operation may
be low pass filtering with a time constant of 10 seconds.
[0047] FIG. 3 illustrates the flow estimate methodology with
respect to a controller or processor 312. A measured pressure value
signal 302 (p(t)) and a measured frequency value signal 304
(.omega.(t)) are input to a flow estimate algorithm 306 for
deriving an estimated flow value signal 308. The flow estimate
algorithm 306 is based on any of the calculations or functions as
previously discussed such as one or more flow lookup tables
330.
[0048] An estimate of flow (e.g., estimated patient respiratory
flow) made by any of the methods discussed herein may then be used
in any suitable flow-based determinations typically made by a
pressure treatment device. For example, the derived flow estimate
can be used to make a change in pressure upon detection of features
of the patient respiratory cycle. In an illustrative embodiment,
the derived flow estimate may be used to trigger an expiratory
pressure relief. In such an embodiment, a ratiometric trigger
threshold, such as a trigger threshold that is a function of the
peak respiratory flow, may be utilized to detect the onset of
expiration. Utilizing such a trigger in particular combination with
any of the above estimates of flow that might deviate marginally
from actual patient flow provides for a more reliable or resilient
respiratory cycle detection and appropriate pressure response.
[0049] In this embodiment, the technology can be implemented
according to the following pseudo code: [0050] if
(RespiratoryFlow>PeakRespiratoryFlow/Y) or (EPR has been on for
over 15 sec) then Turn EPR off [0051] else if
(RespiratoryFlow<0) then Turn EPR on
[0052] Where: [0053] RespiratoryFlow is a derived flow estimate
made by any of the methods previously described; [0054]
PeakRespiratoryFlow is a pre-peak respiratory flow value, such as a
peak determined in a prior respiratory cycle; [0055] Y is some
divisor of the peak respiratory flow (e.g., 4); and [0056] EPR is a
procedure that implements a reduction in the delivered treatment
pressure setting for patient comfort.
[0057] In this embodiment, a bi-level pressure treatment therapy
may be generated such that a reduced pressure level is delivered by
the EPR during patient expiration and a higher treatment pressure
level without the EPR reduction is delivered during patient
inspiration. Depending on the flow generator characteristics or
settings, such as a motor fall time and rise time, the changes
between an inspiratory level and an expiratory level may be gradual
such that a smoother pressure change between the inspiratory
pressure treatment levels and the expiratory pressure treatments
may be effected.
[0058] An example pressure waveform that may be delivered in
accordance with the present technology is illustrated in the graph
of FIG. 4. FIG. 4 includes a plot of a patient simulation flow
waveform 402 that has been generated by a patient flow simulation
apparatus. The patient flow simulation apparatus was coupled with
the patient interface of a pressure treatment device that
implements flow estimation technology described herein. FIG. 4 also
includes a graph of a pressure waveform 404 generated using the
flow estimation and triggering technology discussed herein within
the pressure treatment device. The graph illustrates that the
device may deliver pressure adjustment in synchrony with the cycle
of the patient simulation flow waveform 402 based on the estimated
flow methodology.
[0059] A pressure treatment device can be affected by changes to
pressure in the system introduced by the patient's respiratory
cycle. In the event that the sensors utilized for control of
pressure levels to the mask of the patient interface are located
proximate to the flow generator, rather than the mask of the
patient interface, undesirable swings in mask pressure can be
induced by the patient's respiration. These undesirable mask
pressure swings can be adjusted with the controller to maintain
more steady pressure levels by utilizing the present estimated
patient flow technology.
[0060] For example, in another embodiment, the pressure treatment
device controls pressure rather than controlling motor rpm and a
pressure sensor used for the control is located at or proximate to
the flow generator. In the embodiment, the measure of pressure that
will be used in the feedback loop for pressure control is adjusted
as a function of the estimate of flow. This adjustment is
implemented in a predictive manner in an effort to impede mask
swings induced by the patient's respiratory cycle. For example, the
measured control pressure may be adjusted according to the
following method:
MeasuredPressure.sub.adjusted=MeasuredPressure-FlowFactor
[0061] Where: [0062] FlowFactor is a function of an estimate of
flow determined by any of the previously described methods.
[0063] In one embodiment, this function of the estimate of flow may
be multiplying the estimate by a value K, where K is a value that
is different for positive flow (e.g., patient inspiration) and than
for negative flow (e.g., patient expiration). The value for K may
be experimentally chosen for positive and negative flow as desired
to identify optimum values for swing reduction that generate more
steady mask pressure in response to patient respiration.
[0064] The adjusted measure of pressure may then be applied to a
pressure control feedback loop such as a control loop implementing
Pseudo Derivative Feedback (PDF) control as follows:
Error=DesiredPressure-MeasuredPressure.sub.adjusted
MotorCommand=P*Error+I.intg.Error
[0065] Where: [0066] DesiredPressure is a determined treatment
pressure setting such as an inspiratory or expiratory treatment
pressure level; [0067] MeasuredPressure.sub.adjusted is the
adjusted pressure as previously described; [0068] P and I are
factors chosen for translation of the pressure setting to an
adjustment of the current applied to the motor of the flow
generator for adjusting a particular motor's speed based on the
characteristics of the motor.
[0069] Controller components of such swing compensation control are
illustrated in FIG. 5. An estimated flow value or signal is
supplied to a measured pressure adjustor 550 along with a pressure
value or signal measured by a pressure sensor 556. A pressure
setting value or signal is supplied to the servo 552 along with an
adjusted measured pressure value or signal. Based on these signals,
the servo adjusts the motor current for controlling the output or
speed of the motor 554 of the flow generator to thereby adjust the
pressure delivered by the flow generator device to predictively
reduce mask pressure swings induced by patient respiration.
[0070] In a still further embodiment, swing compensation control
may be implemented with a modified version of the swing control
equation. In such an embodiment, the pressure at the flow generator
is controlled by comparing a desired pressure set point with the
measurement from the pressure sensor. In other words, the flow
generator may be controlled so that a pressure set point is equal
to a measure of pressure determined from a pressure sensor at the
flow generator.
[0071] However, because the pressure at the flow generator is
controlled to the set point, the pressure fluctuations at the mask
are a result of the flow related pressure drop through the patient
interface or delivery circuit. This may be represented by the
following equation:
MaskPres=PresSetPoint-PresLossInDeliveryCircuit
[0072] Where: [0073] MaskPres is the pressure in the patient mask
or patient interface, [0074] PresSetPoint is a desired pressure or
target pressure, [0075] PresLosslnDeliveryCircuit is a pressure
loss due to the impedance of the delivery circuit.
[0076] Pressure fluctuations in the mask can be reduced by
modifying the measured pressure as previously described as
follows:
MeasuredPressure.sub.adjusted=P.sub.M-FlowFactor
[0077] where [0078] P.sub.M is a measure of pressure from a sensor
such as a pressure transducer. The FlowFactor may represent the
pressure drop in the delivery circuit and can be assumed to be
proportional to an estimate of flow. For example,
[0078] FlowFactor=ImpedOfDeliveryCir*Flow
[0079] where [0080] ImpedOfDeliveryCir is the impedance of the
delivery circuit or patient interface, [0081] Flow is an estimate
of flow as previously determined.
[0082] However, since the estimate of flow may be considered to be
a function of the pressure drop across the flow generator as
previously described, then the pressure drop can be approximated to
be proportional to the estimate of flow according to the following
equation:
Flow=PresDropAcrossTurbine/ImpedanceOfTurbine; [0083] where [0084]
PresDropAcrossTurbine is a pressure drop across the flow generator
such as one determined as a difference between a measured pressure
and a derived pressure as previously described (e.g.,
P.sub.M-P.sub.RPM.sub._.sub.derived), and [0085] ImpedanceofTurbine
is an impedance of the flow generator which may depend on the
particular design of the flow generator and may be predetermined
and/or preset into the memory of the controller of the system.
[0086] By combining the preceding flow factor equation with this
immediately preceding flow equation, an explicit computation of one
of the previously described estimates of flow need not be made for
swing compensation. Rather, the determination may be implicitly
implemented when considering the following:
FlowFactor=PresDropAcrossTurbine*ImpedOfDeliveryCir/ImpedanceOfTurbine
[0087] By applying this FlowFactor to the equation for the adjusted
measure of pressure, a further expression may be obtained for the
adjustment in measured pressure as follows:
MeasuredPressure.sub.Adjusted=P.sub.M-K*PressureDropAcrossTurbine
[0088] where [0089] K is a ratio of two impedances such as
ImpedOfDeliveryCircuit divided by the ImpedanceOfTurbine.
[0090] Such an equation may then be implemented for swing
compensation control in a pressure treatment delivery device of the
present technology by controlling the respiratory treatment
apparatus to generate pressure so that the adjusted measure of
pressure meets a target or desired pressure setting.
[0091] In the foregoing description and in the accompanying
drawings, specific terminology, equations and drawing symbols are
set forth to provide a thorough understanding of the present
technology. In some instances, the terminology and symbols may
imply specific details that are not required to practice the
technology. Moreover, although the technology herein has been
described with reference to particular embodiments, it is to be
understood that these embodiments are merely illustrative of the
principles and applications of the technology. It is therefore to
be understood that numerous modifications may be made to the
illustrative embodiments and that other arrangements may be devised
without departing from the spirit and scope of the technology.
[0092] For example, the flow estimate technology may be implemented
in a system utilized for detecting patient flow limitation or
making other adjustments to the delivered treatment pressure of a
pressure treatment device. Moreover, the flow estimate may be
utilized in systems having a flow sensor. In such a system, the
flow estimate technology described herein may serve as back up flow
determination in the event of failure of a flow sensor that is used
for flow based determinations. Alternatively, the estimate of flow
data may be combined with data from a flow sensor to generate
combined flow data to insulate the system from more transient
errors in either the flow signal from the flow sensor or the
derived estimate of flow described herein.
* * * * *