U.S. patent number 3,834,381 [Application Number 05/283,915] was granted by the patent office on 1974-09-10 for compliance compensated ventilation system.
This patent grant is currently assigned to Puritan-Bennett Corporation. Invention is credited to Kenneth M. Peterson.
United States Patent |
3,834,381 |
Peterson |
September 10, 1974 |
COMPLIANCE COMPENSATED VENTILATION SYSTEM
Abstract
Method and apparatus for maintaining a substantially constant
volume of gas flow to a patient, particularly an infant, with a
volume-limited ventilation system, regardless of changes in the
pressure and compliance of the delivery system or patient. The
delivery pressure is monitored and combined with corrective factors
derived from compliance changes in the system, gas heating under
pressure, initial gas pressure, and gas overflow due to inherent
system delays. The combined corrections are used to compute a
compliance-compensation volume which is the volume of gas trapped
within the gas delivery system. The compliance compensation volume
is subtracted from the apparent volume of gas delivered to the
system to determine the volume of gas actually delivered to a
patient. The delivered volume is then compared with a desired
reference volume and is terminated when they are equal.
Inventors: |
Peterson; Kenneth M. (Venice,
CA) |
Assignee: |
Puritan-Bennett Corporation
(Kansas City, MO)
|
Family
ID: |
23088116 |
Appl.
No.: |
05/283,915 |
Filed: |
August 25, 1972 |
Current U.S.
Class: |
128/204.21;
73/861.02 |
Current CPC
Class: |
A61M
16/024 (20170801); A61M 2016/0027 (20130101); A61M
16/0075 (20130101); A61M 2016/0033 (20130101); A61M
2230/46 (20130101) |
Current International
Class: |
A61M
16/00 (20060101); A61m 016/00 (); G01d
005/14 () |
Field of
Search: |
;128/145.5,145.6,145.7,145.8,188,2.08 ;417/274,4,14,12,302 ;60/52
;73/194E |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Gaudet; Richard A.
Assistant Examiner: Dunne; G. F.
Attorney, Agent or Firm: Fulwider Patton Rieber Lee &
Utecht
Claims
I claim:
1. A method of compliance compensation for a volume-limited
ventilator, comprising the steps of:
monitoring the apparent volume delivered by the ventilator;
monitoring the delivery system pressure of the ventilator;
computing an intermediate compliance volume determined by the
algebraic product of said system pressure and a total machine
compliance of the ventilator;
deriving a time-decreasing compensation factor dependent upon the
substantially transient heating of said gas due to rapid system
pressurization;
multiplying said intermediate compliance volume by said
time-decreasing compensation factor to produce a compensated
compliance volume; and
subtracting said compensated compliance volume from said apparent
volume to determine the actual delivered volume of said
ventilator.
2. A method of compliance compensation as defined in claim 1, and
further including the steps of
independently subtracting said compensated compliance volume from
said apparent volume to determine independently an approximation to
said actual delivered volume;
differentiating said independently determined approximate delivered
volume to determine the flow rate of said approximate delivered
volume; and
using said flow rate to correct said actual delivered income.
3. A method of compliance compensation as defined in claim 1,
including the steps of:
comparing said actual delivered volume with a predetermined desired
volume; and
terminating volume delivery when said delivered volume equal said
desired volume.
4. The compliance compensation system of claim 1, including:
means for comparing said actual delivered volume with a
predetermined desired volume; and
terminating volume delivery when said delivered volume equals said
desired volume.
5. A method of compliance compensation for a volume limited
ventilator, comprising the steps of:
monitoring the apparent volume delivered by the ventilator;
monitoring the delivery system pressure of the ventilator;
computing an intermediate compliance volume determined by the
algebraic product of said system pressure and a total machine
compliance of the ventilator;
compensating said intermediate compliance volume for the heating of
said gas under said system pressure by multiplying said
intermediate compliance volume by the factor
1-Ae.sup..sup.-(t/T )
where
A is an empirically derived constant for each ventilator,
t is the time, and
T.sub.c is the thermal cooling time constant of the gas in the
ventilator
the result being a compensated compliance volume; and
subtracting said compensated compliance volume from said apparent
volume to determine the actual delivered volume of said
ventilator.
6. A method of compliance compensation as defined in claim 5, and
further including the steps of:
independently subtracting said compensated compliance volume from
said apparent volume to determine independently an approximation to
said actual delivered volume;
differentiating said independently determined approximately
delivered volume to determine the flow rate of said approximate
delivered volume; and
using said flow rate to correct said actual delivered volume.
7. A compliance compensation system for a volume-limited ventilator
comprising:
means for monitoring an apparent volume delivered by the
ventilator;
means for monitoring delivery system pressure of the
ventilator;
means for computing an intermediate compliance volume determined by
the algebraic product of said system pressure and a total machine
compliance of the ventilator;
means for deriving a time-decreasing compensation factor dependent
upon the substantially transient heating of said gas due to rapid
system pressurization;
means for multiplying said intermediate compliance volume by said
time-decreasing compensation factor to produce a compensated
compliance volume; and
means for subtracting said compensated compliance volume from said
apparent volume to determine the actual delivered volume of said
ventilator.
8. The compliance compensation system of claim 7 including:
means for independently subtracting said compensated compliance
volume from said apparent volume to independently determine an
approximation to said actual delivered volume;
means for differentiating said independently determined approximate
delivered volume to determine the flow rate of said approximate
delivered volume; and
means for using said flow rate to correct said actual delivered
volume.
9. A compliance compensation system for a volume limited ventilator
comprising:
means for monitoring an apparent volume delivered by the
ventilator;
means for monitoring delivery system pressure of the
ventilator;
means for computing an intermediate compliance volume determined by
the algebraic product of said system pressure and a tool machine
compliance of the ventilator;
means for compensating said intermediate compliance volume for the
heating of said gas under said system pressure by multiplying said
intermediate compliance volume by the factor
1-Ae.sup. .sup.-(t/T )
where
A is an empirically derived constant for each ventilator,
t is the time, and
T.sub.c is the thermal cooling time constant of the gas in the
ventilator
the result being a compensated compliance volume;
means for subtracting said compensated compliance volume from said
apparent volume to determine the actual delivered volume of said
ventilator;
means for independently subtracting said compensated compliance
volume from said apparent volume to independently determine an
approximation to said actual delivered volume;
means for independnetly subtracting said compensated compliance
volume from said apparent volume to independently determine an
approximation to said actual delivered volume;
means for differentiating said independently determined approximate
delivered volume to determine the flow rate of said approximate
delivered volume; and
means for using said flow rate to correct said actual delivered
volume;
10. The compliance compensation system of claim 9 including:
means for comparing said actual delivered volume with a
predetermined desired volume; and
terminating volume delivery when said delivery volume equals said
desired volume.
Description
BACKGROUND OF THE INVENTION
The present invention relates generally to respiration systems and,
more particularly, to volume-limited ventilators wherein a measured
volume of gas is delivered to a patient during each inhalation of a
positive pressure breathing system.
Respiration apparatus for positive-pressure breathing therapy and
related applications is well known in the art, and it is common
practice to determine the volume of gas actually delivered to a
patient by making measurements within the respirator. However, when
there are changes in the patient's condition or in the system
compliance itself, the gas volume reaching the patient does not
remain constant. This is due mainly to pressure differences between
the patient and the system. As the elimination of carbon dioxide is
very dependent on tidal volume, such changes in the volume of gas
delivered to the patient can result in rapid abnormalities in a
patient's blood chemistry.
Various attempts have been made to introduce corrections to offset
such tidal volume changes, and these attempts have proven very
satisfactory for ventilators used with adult patients. However,
even greater accuracy is desirable in making corrections for infant
ventilators. This is because of the relatively low tidal volumes of
such infants, compared to the compliance volume of the ventilating
machine itself.
Thus, those concerned with the development of volume-limited
ventilation equipment, particularly for use with infants, have
recognized the need for an improved compliance compensating
technique with enhanced reliability and sensitivity, particularly
for use on infant ventilators. The present invention fulfills this
need.
SUMMARY OF THE INVENTION
The present invention provides a new and improved method and
apparatus for compliance compensation in a volume-limited
ventilation system, wherein a number of factors influencing changes
in tidal volume are monitored and correction signals generated and
combined to calculate a compliance compensation volume. The
compliance compensation volume is then subtracted from the apparent
volume delivered by the ventilator to determine the actual gas
volume delivered to a patient. Heretofore unconsidered factors,
such as the effects of gas heating during pressurization, are
incorporated into the corrections to enable the calculation of
actual delivered gas volume to substantially improved accuracy and
reliability. Such accuracy permits maintaining the relatively low
tidal volume of infants substantially constant.
In a presently preferred embodiment of the invention, the apparent
volume of gas from a suitable volume generator is continuously
monitored, together with the delivery system pressure. The delivery
system pressure is multiplied by a separately computed factor
representing total machine compliance, the product representing an
intermediate compliance volume. The intermediate compliance volume
is further modified to account for the effects of gas heating due
to rapid pressurization. The result is the compliance compensation
volume representing the volume of gas trapped in the system, and is
subtracted from the apparent volume to arrive at the actual gas
volume delivered to a patient. This delivered gas volume is
compared to a preselected desired gas volume and, when the two
quantities are equal, gas delivery is terminated.
In addition to delivery system pressure changes, the volume of
delivered gas is influenced by the positive or negative pressure
existing in the system during the expiration phase, e.g. when a
"Positive End-Expiratory Pressure" technique is employed. The
initial remaining compliance volume is therefore tracked during
expiration, and its value at the onset of inspiration is held and
added to the correction of the delivered volume.
Further, because the gas shut-off devices normally exhibit a time
delay in their operation, gas delivery may not cease immediately
when an "end inspiration" signal is generated. Therefore a
separate, flow-dependent correction signal is generated to
effectively cause the generation of the "end inspiration" signal at
an earlier time.
In the presently preferred embodiment of the invention, machine
compliance is dependent upon the delivered volume. In the case of
an infant respirator, this factor must be included in the
calculation of machine compliance.
Thus the method and apparatus of the present invention provide a
compensated compliance system of enhanced accuracy and reliability
in maintaining substantially constant tidal flows, particularly
when, such as in the case of infants, the tidal flow is relatively
small compared to the machine compliance.
DESCRIPTION OF THE DRAWING
FIG. 1 is a combined diagramatic and electrical block diagram
illustrating the invention; and
FIG. 2 is a flow diagram illustrating the steps of the new and
improved method of the invention.
DESCRIPTION OF THE PREFERRED EMBODIMENT
The operation of the invention is illustrated by FIG. 1 of the
drawing. The method and apparatus of the invention are basically
designed for use with a volume-limited respiration machine which is
only briefly and schematically illustrated in FIG. 2. A more
detailed description of the operation of such respiration machines
is amply described in the literature and particularly in U.S. Pats.
Nos. 3,221,734; 3,368,555 and 3,385,295, which are incorporated by
reference in this application as background information, but are
not required for an understanding of the invention.
As shown in FIG. 1, a volume-limited respirator includes a gas
volume generator which may be in the form of a bellows 10, but is
not limited to that configuration. The forced collapse of the
bellows 10 delivers contained gas to a gas delivery system 12,
represented schematically by a tube. The gas is delivered to a
receiver 14, such as a patient, by any well known device used in
the respiration art, such as face masks, mouth pieces, and the
like.
Basically, such respiration systems operate in two phases or
cycles, an inspiration phase in which gas is delivered to the
patient under positive pressure, and an expiration phase in which
gas delivery is terminated and the patient allowed to exhale the
gases by the collapse of his lungs. It is basically the inspiration
phase with which the present invention is concerned, so the
expiration apparatus is not illustrated. Additionally, it is
assumed that the delivery system 12 is equipped with the other
necessary equipment of typical respirators, such as check valves
and the like, which are not illustrated.
The operation of the system typically proceeds as follows: The
bellows 10 is filled with a suitable gas by auxiliary apparatus
(not shown), and when the inspiration phase begins, the bellows 10
is forced to collapse to drive the contained gas through the
delivery system 12 and into the receiver 14. Mechanically linked to
the bellows 10 is a suitable position transducer, such as a
potentiometer 16, connected across a voltage source E.sub.1. A
wiper contact 17 of the potentiometer 16 follows the movement of
the bellows 10 and, therefore, a voltage-analog of the volume of
gas forced out of the bellows appears on the wiper contact. A
second potentiometer 18, also connected across the voltage source
E.sub.1 is manually adjustable to set a reference voltage on its
wiper contact 19. Heretofore, the bellows volume voltage was simply
compared to the reference voltage by some means, such as a
conventional comparator 20, and when the voltages were equal, the
comparator generated an "end inspiration" signal which was used to
terminate the movement of the bellows 10 and start the expiration
cycle.
It will be appreciated that the actual volume of gas delivered to a
patient can differ radically from the apparent volume delivered to
the delivery system 12, as measured by the movement of the bellows
10. Particularly, changes in the compliance of the delivery system
12, i.e., in the capacity of the system 12 to accept the gases
delivered by the bellows 10, and the differential pressures between
the patient and the delivery system 12, can result in a serious
decrease in the actual volume of gas delivered to a patient.
Generally, without compensation, the relationship between the
desired gas volume as set on reference potentiometer 18 is true
only for one set of conditions.
For example, for an adult, the desired gas volume may be 400-600 ml
of gas, while the system may retain only 100 ml at the end of the
inspiration cycle. Changes in the actual delivered volume for such
conditions are relatively easy to detect. For an infant, however,
the desired gas volume may be only 10-30 ml, and the changes in the
respirator delivery system 12 under such conditions become very
difficult to detect.
In the compliance compensation system of the present invention, a
number of corrective factors are combined to calculate with greater
accuracy the compliance volume, or gas remaining in the delivery
system 12, in order to accurately determine the actual gas volume
delivered to the patient. Generally, the compliance volume of the
delivery system 12 is given by the algebraic product of the
delivery system pressure P.sub.m and the total machine compliance
C.sub.m. The system pressure P.sub.m is monitored by a suitable
pressure transducer 22 in the delivery system 12 and the generated
pressure signal is fed over a line 24 to one input of a
conventional electrical network 26 which calculates P.sub.m
C.sub.m, the term C.sub.m being available as a second input to the
network on a line 28.
For some operating conditions, such as when an adult is being
ventilated, the total machine compliance C.sub.m may be treated as
a constant; the error introduced by changing bellows compliance may
be considered negligible. But when an infant is being ventilated,
the machine compliance, C.sub.m, must be calculated as accurately
as possible, and the bellows compliance is then significant. Thus
the total machine compliance is a constant K.sub.1 minus a second
term dependent on apparent bellow compliance change K.sub.2 V.sub.a
or:
C.sub.m = K.sub.1 - K.sub.2 V.sub.a
It should be appreciated that the actual constant values are
dependent on the type of ventilator being used and are empirically
derived.
The total machine compliance (C.sub.m) signal is derived from a
summing amplifier 30 with a constant voltage from voltage source
E.sub.1 applied to one input line 32 with a multiplication factor
of K.sub.1, and the apparent volume signal V.sub.a from
potentiometer 16 applied to a second input line 34 with a
multiplication factor of -K.sub.2.
It has been found that, for the relatively low volumes of air
delivered to an infant, a significant error is introduced when the
delivery system 12 is rapidly pressurized, e.g. during high flow.
The gas is heated by the pressurization, further increasing the
indicated pressure and erroneously increasing the calculated total
volume of gas in the delivery system 12. However, following initial
heating, the gas cools, and for slow pressurization, e.g. low flow
conditions, the heating error is negligible. Therefore, the cooling
of the gas, an exponential function, is included in the calculation
of the heating error factor.
It is known that the pressure overshoot due to heating follows the
eponential function
A.sub.e .sup..sup.-(t/T )
where:
A is an empirical constant dependent upon the gas and its
container
t is time in seconds, and
T.sub.c is the thermal time constant of the machine-enclosed gas,
and is dependent on the gas and delivery system
characteristics.
The intermediate calculated compliance volume P.sub.m C.sub.m
available on the line 36 is corrected for the thermal pressure
increase by multiplying the term by:
1 - A.sub.e .sup..sup.-(t/T )
which lowers the calculated compliance volume by the amount of
thermal pressure increase, so that the volume of the delivered,
cooled gas will be substantially correct.
In the presently preferred embodiment of the invention, the
intermediate compliance volume P.sub.m C.sub.m is on a line 36
which is fed to a suitable conventional network 38 for multiplying
P.sub.m C.sub.m by the heating compensation factor. The output of
network 38 is then the heat compensated compliance volume and is
fed through a line 40 to a first input of a summing amplifier 42
with an empirically derived multiplying factor -K.sub.3. The
compensated compliance is normally subtracted from the apparent
volume signal connected through line 34 to a second input to the
summing amplifier 42 with an empirically derived multiplying factor
of +K.sub.5 to generate a signal indicative of the delivered gas
volume.
However, a further error which has to be corrected results when the
desired volume is reached and the inspiration cycle is completed.
The pneumatic and electrically operated valves on the respirator
cannot close instantaneously in response to the "end inspiration"
signal on line 21. Therefore, an unwanted additional volume of gas
will be delivered to the patient. The amount of additional gas is
dependent upon the rate of flow of the gas out of the system. This
additional gas is prevented from reaching the patient by adding to
the calculated amount of gas a signal proportional to the
calculated rate of flow of gas out of the system. The "end
inspiration" signal is then generated slightly earlier in time and
the total volume of delivered gas is that desired.
In the illustrated implementation of the invention the compensating
factor for flow rate is derived by first independently calculating
an approximation to delivered gas volume by subtracting the heat
compensated compliance volume signal on line 40 from the apparent
volume on line 34 from the bellows potentiometer 16. These two
signals are fed on lines 44 and 46, respectively, to the inputs of
a summing amplifier 48 which have multiplication factors -K.sub.3
and K.sub.5, respectively.
The resulting approximate-delivered-volume signal is connected
through a line 50 to a conventional differentiator 52, and the
generated flow rate signal is connected through a line 54 to a
third input to the summing amplifier 42 with a derived multiplying
factor of +K.sub.6.
Under some conditions the system pressure P.sub.m may remain above
atmospheric pressure at the end of the expiration phase, and an
erroneous compliance volume signal will be fed to the summing
amplifier 42. As an example, in some respirator applications, a
technique known as "Positive End-Expiratory Pressure" or "PEEP" is
used. In this technique, the patient's expiration is intentionally
stopped at above atmospheric pressure. To correct this error, a
conventional track-and-hold network 58 is connected through a line
60 to the intermediate compliance volume signal on line 24. The
network 58 tracks the intermediate compliance volume during the
expiration phase and then holds that value as an initial compliance
volume error during the inspiration phase. The held compliance
signal is connected through a line 62 to a fourth input to the
summing amplifier 42 with a multiplication factor of K.sub.4 to
correct the generated delivered volume signal. Thus, the delivered
volume will be correctly calculated from an initial compliance
volume starting point of zero, independent of initial pressure at
the onset of the inspiration phase.
The summation of the heat- and compliance-compensated volume signal
on line 40, the apparent volume signal on line 34, the flow rate
signal on line 54 and the held compliance signal on line 62 in
summing amplifier 42 results in an output signal on line 56
indicative of the delivered gas volume to the patient. This signal
serves as a first input to the comparator 20, the second input
being the desired volume signal. When the two are equal, the
comparator 20 generates the "end inspiration" signal on line 21 to
end the inspiration phase and begin the expiration phase.
FIG. 2 illustrates the method of the invention. Following the start
of inspiration, a first step is to monitor the apparent volume
delivered by the bellows. The second step is to calculate the
intermediate compliance volume, followed by the third step of
compensating the intermediate compliance volume for heat.
Concurrently, the fourth step of measuring the flow rate can be
performed.
In the fifth step, the compensating factors are combined into a
compensated compliance volume, and the result subtracted from the
apparent volume to obtain the actual delivered volume to the
patient. In the sixth step, the delivered volume is compared with a
pre-selected desired volume, and when the two are equal, and "end
inspiration" signal is generated to terminate the inspiration phase
and begin the expiration phase.
Thus, the method and apparatus of the present invention provide a
substantially reliable and accurate means for compensating
volume-limited ventilation systems, particularly such systems
designed for ventilating infants. The invention compensates for
changes in patient and system changes to deliver a substantially
constant volume of gas to a patient.
It will be appreciated that while a specific, presently preferred
embodiment of the invention has been described in detail, various
modifications can be made without departing from the spirit and
scope of the invention. Accordingly, it is not intended that the
invention be limited except by the appended claims.
* * * * *