U.S. patent number 3,611,178 [Application Number 04/865,919] was granted by the patent office on 1971-10-05 for pressure-sensing signal generator.
This patent grant is currently assigned to Bourns, Inc.. Invention is credited to Gerald L. McConnell.
United States Patent |
3,611,178 |
McConnell |
October 5, 1971 |
PRESSURE-SENSING SIGNAL GENERATOR
Abstract
Extremely sensitive apparatus for detecting effort of a patient
to inhale and to produce a powerful output signal of very short
duration in response for initiating action of a respirator, with
means immunizing the apparatus against adverse temperature change
effects, means for stabilizing operation of the apparatus, and
means for varying the sensitivity of the apparatus to pressure
differential.
Inventors: |
McConnell; Gerald L.
(Riverside, CA) |
Assignee: |
Bourns, Inc. (N/A)
|
Family
ID: |
25346534 |
Appl.
No.: |
04/865,919 |
Filed: |
October 13, 1969 |
Current U.S.
Class: |
331/65;
128/204.23; 331/117FE; 331/117R; 331/174; 340/626; 340/573.1 |
Current CPC
Class: |
A61B
5/113 (20130101); G01L 9/0072 (20130101); G01L
9/12 (20130101); G01L 23/125 (20130101); G01L
19/04 (20130101); G01L 13/025 (20130101); A61M
16/00 (20130101); A61M 16/021 (20170801); A61M
2016/0021 (20130101) |
Current International
Class: |
A61B
5/11 (20060101); A61B 5/113 (20060101); A61M
16/00 (20060101); G01L 13/00 (20060101); G01L
9/12 (20060101); G01L 23/00 (20060101); G01L
13/02 (20060101); G01L 23/12 (20060101); G01L
9/00 (20060101); A62b 007/04 (); G01n 027/22 ();
H03b 005/12 () |
Field of
Search: |
;331/65,117,174 ;324/61
;328/1 ;73/384 ;340/279,421
;128/2.08,140,142.2,145.5,145.8,422,DIG.17 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Lake; Roy
Assistant Examiner: Grimm; Siegfried H.
Claims
I claim:
1. A pressure-sensing signal generator system adapted to respond to
very small difference between pressures exhibited at two closely
spaced points and to produce an electric signal only immediately
following such response, said system comprising:
first means, including electronic oscillator means, effective
incident to oscillation of the oscillator means to produce an
output signal during such oscillation;
second means, including pressure-sensitive capacitor means
connected to said oscillator means and effective to inhibit
oscillation of the oscillator means during absence of pressure
difference between two points therein and effective incident to
establishment of a pressure difference between said points to
promote oscillation of said oscillator means; and
third means, including feedback means connected to receive an
output signal from said first means, said third means effective
upon receipt of a signal from said first means to quench
oscillation of said oscillator means,
whereby oscillation of said oscillator is quenched following
production of a signal representative of a pressure difference
between said two points, irrespective of continuation of the
pressure difference between said two points.
2. A system as defined in claim 1, in which said third means
comprises potential-sensitive capacitor means shunting said
first-named capacitor means, and means rendered active by said
output signal to apply voltage to said potential-sensitive
capacitor means to increase the capacitance exhibited by the shunt
combination of capacitor means to effect quenching of oscillation
in said oscillator means.
3. A system as defined in claim 2, including adjustable means for
applying an adjustable continuous potential to said
potential-sensitive capacitor means, whereby sensitivity of said
system to pressure differential between said two points may be
adjusted.
4. A system ad defined in claim 1, including means for maintaining
at least an active element of said oscillator means at superambient
temperature, and means for inhibiting oscillation of said
oscillator means pending attainment of said superambient
temperature, whereby said system is inhibited from producing an
output signal until said oscillator means is stable with respect to
variables induced by temperature change.
5. A system as defined in claim 1, including respirator means
connected to receive an output signal produced by said first means
and effective in response thereto to proceed through a cycle of
operation.
Description
BRIEF SUMMARY OF THE INVENTION
a. Background of the Invention
In certain applications of pressure change sensing, it is
imperative to very quickly and positively sense pressure decrease
below ambient or a determined level or value, and to generate a
signal indicative of the change for use in or by an apparatus. For
example, in respirator apparatus adapted for use in relief of
hyaline membrane syndrome and other breathing difficulties
evidenced by neonatal infants, it is of importance to sense very
weak efforts to inhale by the infant and to immediately aid the
infant by supplying air or a special mixture of gases under
superambient pressure to the infant via nasal mask means, and to
thereafter permit free exhalation by the infant at a determined
subsequent time. The effort to inhale causes a drop in pressure,
however slight, at the nostril entrance; and this pressure change
has been utilized, by use of pressure change sensing means, to
initiate action of the respirator to supply or deliver an
accurately measured volume of air, oxygen enriched or otherwise,
under regulatable pressure and at a regulatable speed, to the
infant patient. The respirator is so devised that following
delivery of the air, valve means are operated and exhaling is
accomplished by natural contraction of the chest cavity of the
patient. The same factors are noted in respect of respirator
mechanisms employed for other than neonates. Heretofore various
kinds of pressure transducers have been employed to provide an
output for initiating actuation of respirator means, such
transducers including pressure-sensitive electric switches. Since
the pressure sensor is most desirably situated as close as is
practicable to the nostrils of the patient, whereby sensitivity may
be maximized, and since switch means in proximity to a patient, and
especially near to oxygen or oxygen-enriched air, are undesirable,
designers of respiratory aid systems have had to compromise between
optimum sensitivity and attendant undesirable factors. One
compromise has resulted in the use of sealed reed switch means
operated by a pressure-sensitive means, located distant from the
nasal mask and having a sensitivity much less than is desirable. No
fully satisfactory solution to the problem of providing an
extremely sensitive safe means for rapidly initiating action of the
respirator means incident to an effort to inhale by the patient has
been attained prior to advent of the present invention. Thus, it is
a prime object of the invention herein disclosed in a presently
preferred exemplary form to obviate the noted disadvantages of
prior art devices of the indicated class; and it is a broad object
of the invention to provide improvements in means for initiating
action of respiration-augmenting means. A more specific object is
to provide an extremely sensitive, extremely fast-acting
regulatable means for producing a powerful signal indicative of an
effort of a patient to inhale and which signal can be utilized to
initiate action of other means such as a respirator. Other objects
and advantages of the present invention are hereinafter stated or
made evident in the appended claims and disclosure of the preferred
exemplary embodiment.
b. Brief Description of the Invention
According to the invention, presence of electric switch means in
proximity to the patient is avoided, and extreme sensitivity of
sensor means is concurrently attained, by using electrical
capacitor means, a movable plate or electrode of which is disposed
on a thin resilient membrane or diaphragm which in turn is exposed
on one face to the ambient and on the other to the interior of a
passage closely communicating with the nasal passages of the
patient, as sensor means sensitive to any effort of the patient to
inhale. The capacitive means is connected in the circuit of an
electronic oscillator and is effective to initiate oscillation of
the oscillator incident to very slight change of capacitance as the
diaphragm moves in response to very slight change in differential
pressure as the patient makes an effort to inhale. The oscillator
circuit is so devised that commencement of oscillation results in
transmission of an electric signal which is used to activate or to
initiate activation of means in the respirator system. The
exemplary system comprising the oscillator circuit is further
devised to be self-quenching, whereby the oscillator is quenched
from oscillatory to quiescent status at the end of a brief interval
of time (e.g., 5 milliseconds) next following initiation of
oscillation.
Thus, unless the capacitor means has returned to the neutral
attitude during the signal generation period, the oscillator is
again triggered into oscillation, generates another signal, and
again quenches, and repetitively does so until the capacitor means
returns to the initial neutral attitude and capacitance value. The
signal, in the form of an electric wave, is integrated, preferably
following wave shaping and/or amplification in circuitry of the
system, to produce an output signal for transmission to and
utilization in the respirator. In the respirator, arrival of the
output signal is effective to set in motion cyclical means which
then operates through one cycle during which a measured volume of
air is supplied under moderate superatmospheric pressure to the
nasal mask on the patient over a regulatable period of time which
is followed by a period during which valve means are operated and
the patient exhales. The respirator is so devised that in one mode
of operation the cyclical operation is automatically repeated and
in another mode of operation the cycle is again initiated by
attempted inspiration by the patient. An exemplary circuit
according to the present invention permits variation of the
sensitivity of the detecting means, whereby action is initiated
only in response to subatmospheric pressure in the mask of any
selected value in the range from 0.1 mm. to 5.0 cm. of water
column. Since the oscillator is set into oscillation as the result
of a very small movement of a diaphragm-supported capacitor
electrode, the circuit can be employed to detect a very small
mechanical movement of a part connected to the electrode. The
circuit is so arranged that capacitive means including the
pressure-sensitive capacitor means, herein termed the principal
capacitor, are in shunt with the oscillatory circuit of the
oscillator, the capacitive means further comprising a variable
capacitor in the form of a voltage-variable capacitor whereby the
effective value of the shunt capacitance may be varied by varying
the potential applied across the later capacitor. The circuit
preferably includes an amplifier which provides a strong output
signal during oscillation of the oscillator; and a portion of the
output signal is fed back via signal-delay means to the
voltage-variable capacitor to change the shunt capacitance to a
value that causes rapid decay and extinction or quenching of the
oscillation of the oscillator after a determined period of time.
Since return of the capacitor to a capacitance value at which
oscillation is initiated will not generally cause the oscillator to
stop oscillating, the feedback quenching of the oscillator permits
of greatly increasing sensitivity of the signal generator to change
of pressure at the movable portion of the principal capacitor. To
enhance stability of operation and sensitivity, the active elements
of the oscillator are temperature stabilized by enclosing them in
an oven that is maintained at a temperature somewhat above room
temperature, e.g., at 80.degree. C.
The preferred voltage-variable capacitor is a voltage-sensitive
diode; and the preferred active element of the oscillator is a
field-effect transistor. A trimming or adjusting capacitor is
provided for initial adjustment of the oscillator. A preferred form
and arrangement of components of an exemplary pressure-sensitive
signal generator is depicted in schematic form in connection with a
known respirator in the accompanying drawings.
DESCRIPTION OF THE DRAWINGS
In the drawings,
FIG. 1 is a functional block diagram of an exemplary system
according to the invention;
FIG. 2 is a fragmentary sectional view of the exemplary
pressure-sensitive capacitor comprised in the capacitive shunt
connected to the oscillator of the system; and
FIG. 3 is a detailed circuit diagram of the signal generator part
of the system.
DETAILED DESCRIPTION OF THE INVENTION
Referring first to FIG. 2, there is illustrated in section a
pressure-sensitive capacitor device or sensor adaptable to
delicately sense change of pressure from ambient atmospheric
pressure to a lower value. The drawing is essentially schematic and
to not specific scale. The sensor comprises means in the form of a
box 10 providing a chamber sealed at the peripheral juncture
between the body 10b and cover 10c of the box. Disposed in body 10b
is a rigid stop device 12 formed of molded material. The stop and
box body 10b are bored to provide an opening for reception of a
conduit 14 which is supported by the body and communicates with the
mentioned nose mask (not shown) which is per se not of the present
invention and may be of the type illustrated in U.S. Pat. No.
3,357,428 or that illustrated in U.S. Pat. No. 1,206,045, for
examples. The cover 10c is of insulation and is similarly bored to
receive and support an conduit 16 which is open to the ambient
atmosphere. The box is preferably of circular plan form, and has
secured thereto at the interior periphery along the juncture of the
cover and body a thin resilient diaphragm 20. The diaphragm
overlies a centrally perforated circular metal electrode 18a which
is affixed to cover 10c and forms one electrode of a principal
capacitor herein denoted C1 in the circuit diagram. A second metal
plate 18b, complementary to plate 18a and which may be formed of a
film of metal formed on the diaphragm, serves as a movable
electrode of capacitor C1. Flexible conductors 22a and 22b,
connected as indicated in the drawings, serve as respective
terminal connectors for the capacitor plates. An extension of cover
10c serves as a base for support of an enclosure 24 in which other
components of the signal generator may be housed, as on a circuit
board.
As is evident, when air exits from the chamber above diaphragm 20
incident upon an effort by the patient to inhale consequent
reduction of pressure in conduit 14, the diaphragm will be forced
to move in the direction away from electrode 18a under the
influence of the ambient air and its pressure in the chamber below
the diaphragm. Thus the capacitance of capacitor C1 is lessened or
decreased. The slight change in capacitance is employed to initiate
action of circuitry connected to capacitor C1 as shown in detail in
FIG. 3 and in block diagram form in FIG. 1.
Referring to FIGS. 1 and 3, the capacitor unit 30 comprising
pressure-sensitive capacitor C1 is connected to serve as the
primary control component, in shunt to an oscillator unit 40. The
oscillator unit, herein termed the oscillator in the interest of
brevity, comprises tapped inductor L1, capacitor C2, resistor R1
and field-effect transistor Q1, all connected as a Hartley
oscillator. Closely regulated or constant-potential DC power is
supplied as from a battery B by way of lead P1 (negative) and
ground (positive) as indicated. An oscillator trimming unit 50
comprising variable capacitor C2 is connected as a feedback control
in the oscillatory circuit of unit 40, as shown. Thus the
oscillator capacitance can be adjusted to a proper value to permit
quenching and oscillation initiation as will presently be
described.
A temperature-regulating unit 60 which comprises a heater Rx of the
negative resistance type such as is sold under the trade name
KLIXON is housed, together with temperature-sensitive components of
the oscillator, in an insulated chamber or over H. Thus the unit
60, connected as shown and arranged as described, if effective when
energized to raise the temperature in which the
temperature-sensitive components operate to a superambient value,
e.g., 80.degree. C.; and to maintain those components at that
constant temperature. Thus the oscillator is immunized against
adverse changes due to change in ambient temperature. The oven H is
not shown in detail since it may be one of many kinds commercially
available or may be merely an insulated box. While in the drawing
only the transistor Q1 is shown in the oven with the heater
thermostat, it will be understood that all components of the
oscillator may be so housed.
When the oscillator is permitted to oscillate, it produces a
high-frequency wave output. The circuit component values are such
that at each alternate half-cycle of the oscillation of the
oscillatory circuit the transistor Q1 quickly becomes saturated,
whereby the output to a coupling capacitor C4 is of substantially
square wave form. An exemplary oscillator frequency is 30
megahertz. Oscillation of the oscillator is permitted only under
special circumstances, and at other times is prevented by one or
more actions of means presently described.
The square wave output signal passed through coupling capacitor C4
is subjected to rectification in a rectifier-integrator unit 70
which comprises diodes CR1 and CR2 and capacitor C5. The effect of
the units 70 is to supply to the gate of the transistor Q2 of an
amplifier unit 80 a bias which causes or permits Q2 to conduct
during the duration of the square wave signal. Thus during that
period a negative-going pulse appears on output signal lead P2.
That output signal is transmitted to and utilized in the respirator
unit 90. For example, the negative-going pulse may be of the order
of 5 milliseconds duration and may be used to pull up a latching
relay which initiates a cycle of action of the respirator. The
respirator may be, for example, like or similar to those disclosed
in U.S. Pat. Nos. 3,357,427 and 3,006,336; or similar
breathing-augmentor apparatuses.
Once a cycle of operations has commenced or been initiated by the
output signal, air under pressure is forced into the mask and the
pressure in the chamber above the sensor diaphragm 20 (FIG. 2)
increases to a superambient value and the capacitance of capacitor
C1 is increased at least to its original value. However, that alone
does not preclude continued oscillation of the oscillator; hence
means are provided for quenching the oscillator after oscillation
has continued for a period sufficient to insure relay pullup or
other initiation of respirator operation. Such a period has herein
been selected, for example, to be of the order of 5
milliseconds.
Amplifier transistor Q2 is normally biased off by bias supplied by
bias unit 100 which comprises resistors R2 and R3 connected as
indicated in FIG. 3. Thus the amplifier unit will not provide an
output signal until the bias provided by the bias unit 100 is
overcome by the input signal from the unit 70. When an amplifier
unit output signal is produced and transmitted to the respirator
unit 90, a quenching signal unit 110 also receives the amplifier
output signal, via branch line P2'. The quench pulse unit comprises
resistor R4, capacitor C6, transistor Q3, and connections as shown.
The negative-going pulse signal is effective to build up a charge
on capacitor C6, via resistor R4 connected to line P2'. When the
potential across C6 reaches a determined value, transistor Q3 is
biased to conduction. Transistor Q3 is normally biased off by a
biasing unit 120 which comprises resistors R5 and R6 and
connections as indicated.
When the quenching signal unit transistor Q3 has thus been induced
to conduct following an amplifier output signal duration of the
noted character, a current signal is produced which is transmitted
via line P3 and the resultant potential change is transmitted via
radiofrequency choke coil L2 to a voltage-sensitive capacitor CRX
comprised in an oscillator quench unit 130. Capacitor CRX in series
with auxiliary capacitor C7 forms a variable capacitive shunt to
ground for the oscillatory circuit of unit 40. The arrangement is
such that with substantially no DC potential applied across
capacitor CRX, the oscillator will commence oscillating as soon as
the capacitance of sensor capacitor C1 falls slightly incident to
the patient's attempting to inhale. Thus, with the oscillator
oscillating, a current signal is produced by Q3 after about 5
milliseconds oscillation. The current signal produces a
potential-drop signal which has the effect of increasing the
capacitance exhibited by CRX to the extent that oscillation of the
oscillator is damped and quenched, even if sensor capacitor C1 has
not yet returned to maximum value. THus the oscillation ceases and
the amplifier output signal to the respirator unit decays to
substantially zero volts value. If the respirator has not
responded, decay of the amplifier output signal and consequent
decay of the quench signal permits immediate resumption of
oscillation if subatmospheric pressure prevails in the nose mask on
the patient. Repetition of the oscillation-signaling cycle within a
few milliseconds is of no significance if the respirator is
proceeding through a cycle but has not yet produced superambient
pressure on the upper surface of the sensor diaphragm 20, since the
latching relay in the respirator has previously been pulled in and
is holding. If for some reason the respirator failed to respond to
the initial amplifier output signal, a new oscillation is promptly
initiated and a repetitive signal transmitted to the respirator.
Thus operation of the respirator is insured.
To prevent operation of the oscillator until the components have
reached the desired constant operating temperature, a warmup timer
circuit or unit 140 is incorporated and is effective to maintain a
high capacitance value at CRX to bar oscillation in unit 40 for a
determined period of time sufficient for the oscillator to become
temperature-stable. Unit 140 comprises a transistor Q4, capacitor
C8 and resistor R8. When the power circuit is closed as by switch S
to energize the system, Q4 immediately conducts, current flowing
from lead P1 via a selected portion of a variable resistor R9,
through Q4 to ground. Thus potential is supplied via resistor R7
and choke L2 to voltage-sensitive capacitor CRX, raising that
capacitance to a level sufficient to prevent oscillation of the
oscillator of unit 40. After a time determined by the values of R8
and C8, transistor Q4 is biased off by the potential of the charge
accumulating on C8, the capacitance of CRX falls to a value
permitting oscillation to commence, and the system is ready to
sense inspiratory effort of a patient and initiate respirator
operation. The values of C8 and R8 are selected such as to permit
the heater of unit 60 to bring the oscillator to the desired
temperature within, for example, 5 minutes. Levels at which CRX is
caused to quench, or permit operation of, the oscillator of unit 40
are set by adjustment of the values of variable resistors R9 and
R10 comprised in a sensitivity control unit 150.
The nose mask used in conjunction with respirator unit 90 may be of
a type now commercially available, or may be such as is disclosed
in U.S. Pat. No. 1,206,045. Exemplary electronic components for the
detailed circuitry shown are as tabulated in table I at the
conclusion of this specification.
The preceding description makes it evident that the capacitance
change at capacitor C1 necessary to trigger the oscillator can be
made very small by adjustment of the sensitivity unit, since that
change can be very much less than the opposite change at C1 that
would be necessary to quench the oscillator, and quenching is
brought about by a powerful action of voltage-sensitive capacitor
CRX initiated by the quench pulse unit 110. Thus even the very
feeble effort of a neonate to inhale while suffering hyaline
membrane syndrome or other respiratory distress is sufficient to
initiate positive respirator action. Further, the system is
extremely stable and immune to effects of changing temperature of
the ambient. Also it is evident the negative-pressure level at
which action is initiated is adjustable by varying the resistor
means of the sensitivity unit. The time period between successive
oscillator signals is regulatable by change of the feedback circuit
component values such as C6-R4 and R6-R5. The pressure differential
at the diaphragm 22, required to change the capacitance of C1
sufficiently to initiate oscillation can, by virtue of the
adjustability of the sensitivity control unit 150, be varied over
wide limits e.g., from 0.1 mm. to 5.0 cm. water column. Thus the
system is of value not alone in initiating respiration aid in
response to extremely feeble respiratory efforts, but also in
promoting increasing effort on the part of the patient to breathe
voluntarily. The latter promotion is effected by gradually
increasing the inspiratory effort necessary to initiate oscillation
of the oscillator, by gradually reducing the sensitivity of the
system.
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TABLE I
C1 1-5 pfd. R1 100 K ohms C2 1.5-12 pfd. R2 220 ohms C3 22 pfd. R3
2.7 K ohms C4 3 pfd. R4 100 K ohms C5 0.02 mfd. R5 680 ohms C6 0.02
mfd. R6 2.7 K ohms C7 10 pfd. R7 2.7 K ohms C8 50 mfd. R8 2.2
megohms R9 2.5 K ohms R10 1 K ohms R11 22 K ohms Rx Klixon SST 1-2,
80.degree. C.
cr1 1n34 g.e. cr2 1n34 g.e. crx mv1620 motorola
Q1 MPF 102, Motorola Q2 MPF 102, Motorola Q3 2N1377, Motorola Q4
MPF 102, Motorola
L1 15 closed turns with tap at five turns -22, 0.25" D. L2 22
microhenries
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