U.S. patent number 3,727,606 [Application Number 05/045,688] was granted by the patent office on 1973-04-17 for apnea detection device.
Invention is credited to Ulrich Sielaff.
United States Patent |
3,727,606 |
Sielaff |
April 17, 1973 |
**Please see images for:
( Certificate of Correction ) ** |
APNEA DETECTION DEVICE
Abstract
A device for providing continuous monitoring of a human
breathing and heart rate wherein a fluid-tight mattress is located
in contact with the human and produces pressure signals in response
to the breathing and heart rate. A pressure transducer is provided
for interpreting the pressure signals for application to an
electronic circuit for visual or audible recognition of the
signals.
Inventors: |
Sielaff; Ulrich (McFarland,
WI) |
Family
ID: |
21939332 |
Appl.
No.: |
05/045,688 |
Filed: |
June 12, 1970 |
Current U.S.
Class: |
600/535;
340/573.1; 340/626 |
Current CPC
Class: |
A61B
5/113 (20130101) |
Current International
Class: |
A61B
5/11 (20060101); A61B 5/113 (20060101); A61b
005/02 (); A61b 005/10 () |
Field of
Search: |
;128/2R,2S,2.5R,2.5T,2.5P,2.5B,2.6R,2.6F,2.08,DIG.17
;340/279,240 |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
|
|
|
|
|
|
|
1,480,160 |
|
Apr 1967 |
|
FR |
|
418,067 |
|
Feb 1947 |
|
IT |
|
522,563 |
|
Apr 1955 |
|
IT |
|
673,719 |
|
Oct 1929 |
|
FR |
|
Primary Examiner: Howell; Kyle L.
Claims
I claim:
1. A breathing monitor for continuously detecting movement of a
living infant, comprising a flexible air-tight resilient mattress,
adapted to underlie and support said infant, the interior of said
mattress containing air volumes which in response to bodily
movement of the infant on said mattress are compressed and exhibit
relative pressure fluctuations with respect to the ambient
atmosphere; means communicating with said mattress interior for
receiving said pressure fluctuations and converting said pressure
fluctuations into a recognizable signal; and non-closeable bleed
means connected continuously between said mattress interior and
ambient atmosphere to enable bleeding of relatively slow pressure
fluctuations from said interior.
2. A breathing monitor for continuously detecting movement of a
living infant, comprising a flexible air-tight resilient mattress
adapted to underlie and support said infant, the interior of said
mattress containing air volumes which in response to bodily
movements of the infant on said mattress are compressed and exhibit
pressure fluctuations; valve means communicating with said mattress
interior for receiving said pressure fluctuations, said valve means
being adapted to filter out pressure fluctuations above and below a
predetermined pressure range; and means connected for receiving the
remaining filtered pressure fluctuations from said valve means and
converting said filtered pressure fluctuations into a recognizable
signal.
3. A breathing monitor as defined in claim 2 wherein said valve
means comprises a chamber, said chamber having an inlet and an
outlet, a first check valve means in said chamber adapted to open
said chamber to ambient atmosphere at a predetermined positive
pressure within said chamber, a second check valve means in said
chamber adapted to open said chamber to ambient atmosphere at a
predetermined negative pressure within said chamber.
4. A breathing monitor as defined in claim 3 wherein said
predetermined positive pressure within said chamber is about 0.50
cm water and said predetermined negative pressure within said
chamber is about 0.50 cm water.
5. A breathing monitor as defined in claim 3 wherein said chamber
has an orifice adapted to bleed slow changes in pressure within
said chamber to the ambient atmosphere.
6. A method of monitoring the breathing and heart rate related
movements of an infant, comprising the steps of:
positioning an air-tight pad underlying and supporting the infant
to be monitored,
maintaining the interior of said pad at about ambient atmospheric
pressure,
sensing pressure variations in the pad resulting from movements of
the infant,
receiving the sensed variations and filtering out gross pressure
variations above and below a predetermined pressure range,
monitoring the filtered pressure variations and converting the
filtered variations to a recognizable signal.
Description
BACKGROUND OF THE INVENTION
This invention relates generally to monitoring devices for
maintaining a continuous surveillance of certain vital body
movements and, more particularly, to a device for monitoring the
breathing and heart rate of infants.
Periodic breathing, called apnea, is a respiratory difficulty
particularly prevalent in premature infants where the infant
experiences a temporary stoppage of breathing and, unless the
condition is detected immediately and preventive steps taken, the
lack of continued circulation to the brain may result in serious
damage.
Although the periodic breathing will sometimes correct itself
without assistance to the infant's respiratory system, it is
extremely important that some monitor be provided to continuously
ascertain the breathing and heart rate of infants, in order to
alert hospital personnel to prolonged conditions of apnea so that
the proper measures may be quickly taken to restore continuous,
uninterrupted breathing. A further need for such apnea monitoring
equipment is shown by the unpredictability of an apneac condition,
whereas the periodic breathing or stoppage may occur at any time
and even immediately after a continued surveilance where no
symptoms are evident.
Prior to the present invention, various devices have been devised
to afford continuous breathing and heart monitoring; however, in
general, these devices have relied upon some physical attachment of
electrodes or detectors upon the infant's body and, therefore, have
been susceptible to dislodgement through gross body movements of
the infant, or during movements of the infant by attending
personnel, and a false apnea condition and alarm are
experienced.
In addition, such prior art devices have often required an
electrical connection in some manner between the infant and the
monitoring equipment, thereby presenting a potential electrical
hazard.
It is thus an object of the present invention to provide a highly
sensitive breathing and heart rate monitor which is continuously
capable of detecting apnea conditions in an infant.
It is another object of this invention to provide a sensitive
breathing and heart rate monitor wherein no physical attachment of
any kind is necessary to the infant being monitored.
It is a still further object to provide a continuous breathing and
heart rate monitor where all sensing means associated with the
infant are pneumatically operated, whereby no electrical
connections are utilized.
The aforementioned objects are all achieved by the provision of a
fluid-tight mattress for placement beneath an infant, wherein the
changes in pressure within the mattress due to the breathing and
heart rate of the infant, are converted by a highly sensitive
transducer to an electrical signal which may be used for indicating
or recording the sensed function.
A specific embodiment of the invention has been chosen for purposes
of illustration and description, and is shown in the accompanying
drawings, forming a part of the specification, wherein:
FIG. 1 is a schematic drawing of the overall invention;
FIG. 2 is a schematic drawing of an alternate mattress suitable for
use in the invention;
FIG. 3 is a schematic diagram showing the electronic circuitry, in
block form, which may be used with the present invention.
Referring now to FIG. 1, there is shown a schematic diagram of the
overall apnea monitoring system. The system includes a fluid-tight
flexible pad 10, adaptable for placement beneath an infant. The pad
10 may contain a resilient porous material for support and comfort
of the infant and which allows the free circulation of fluid within
the outer non-porous covering.
A pop-off valve 12, the purpose and function of which will be later
explained, communicates with the interior of the pad 10 through
flexible tubing 14. A transducer 16 is provided and which also is
in fluid communication with the interior of pad 10 by means of
flexible tubing 18, pop-off valve 12, and tubing 14. The transducer
is of the pressure-sensitive type which is adapted to sense a
change in pressure and thereafter experience a predetermined change
in electrical characteristics in response to the sensed pressure
change.
As may now be seen, any pressure fluctuations occurring in the pad
10 are directly transmitted to the transducer 16 where they are
sensed and hereafter converted and transmitted as electrical
signals. The transducer 16 must be capable of detecting minute
pressure changes due to the respiration and heart beat of an infant
resting upon the pad 10; however, such transducers are commercially
available having the required sensitivity.
The transducer used must be extremely sensitive to pressure
variations as the pressure signals experienced from the movement of
infants are extremely minute. As an example, the present invention
has been utilized to monitor the breathing rate of premature
infants weighing less than about 3 pounds, and it is found that the
pressure signals from the fluid-tight mattress are in the order of
from about 0.05 to 0.08 cm of water. These signals were readily
detectable by a pressure transducer.
For infants weighing more than about three pounds, a transducer is
easily capable of detecting both the breathing rate as well as the
heart rate of the infant.
The transducer, therefore, must be capable of distinguishing
pressure signals of minute magnitude and alter its characteristics
in order to provide a sufficient alteration for sensing by a later
fluidic or electronic circuit.
The purpose of the pop-off valve 12 is to prevent large changes in
pressure from the pad 10, such as those caused by gross bodily
movements of the infant, from reaching and affecting the transducer
16. To this purpose, the pop-off valve 12 is provided with a pair
of discs 20 and 22 which are adapted to be displaced with respect
to their respective seats 24 and 26 to allow fluids to pass freely
therethrough.
As shown, the disc 20 is positioned such that a predetermined
negative pressure caused by a gross body movement causes a
displacement of the disc 20, allowing atmospheric pressure to enter
the pop-off valve 12 to equalize the effect of the negative
pressures.
The disc 22 is positioned such that a predetermined positive
pressure caused by the gross body movement displaces that disc 22
and the excess pressure is exhausted to the atmosphere.
Conventional means, such as springs, are provided in order to
return the discs 20 and 22 to their proper seated condition after
the increase or decrease in pressure has been properly equalized,
and also, conventional means may be included for adjusting the
sensitivity of response of each of the discs 20 and 22. In the
preferred embodiment, it has been found that either weight or
spring loaded discs may be suitable and satisfactory results have
been achieved where the valves are preset to be displaced from
their seats at a predetermined positive or negative pressure of
about .+-.0.5 cm water. This value is therefore the largest
positive or negative pressure experienced by the pressure
transducer.
In addition to limiting the effects of large pressure variations
due to gross body movements, the pop-off valve 12 serves to achieve
an equilibrium point during the initiation of the system. The
compression of the pad 10 due to the initial placement of an infant
within an incubator or the like upon pad 10 will cause the disc 22
to be displaced and allow the excess pressure to escape. This
venting of excess pressure will continue automatically until an
equilibrium point is reached, at which time, the system is closed
and small pressure variations; i.e., within .+-.0.5 cm. water will
be completely contained within the system and will act upon the
transducer 16.
Further, very slow fluctuations in pressure, such as by a gradual
temperature change, are bled from the system through orifice 28 in
pop-off valve 12, thereby creating a stable base line reading, yet
the orifice 28 may be adjusted such that rapid fluctuations caused
by the infant's respiration and heart rate are unaffected by its
presence. Although the orifice 28 is shown in the preferred
embodiment located on pop-off valve 12, the actual placement within
the system may vary widely without affecting its operation. The
actual size of the orifice 28 also may vary depending on the
overall design of the system. Its size governs the frequency
response of the system; i.e., where the orifice 28 size is
particularly small, relatively slow fluctuations are detected,
while a large size orifice may entirely exhaust the same slow
fluctuations.
The changes in electrical characteristics of the transducer 16,
responsive to pressure fluctuations in the pad 10, are applied to
electronic circuitry 30 for performing various functions such as
triggering an alarm system at a particular apnea condition or
controlling a read-out device which may be under surveilance by
attending hospital personnel.
Referring now to FIG. 2, there is shown an alternate flexible pad
10 suitable for use in the apnea detection device. Although a
flexible pad 10 of a continuous design, that is, the internal
resilient material is dispersed uniformly and uninterrupted
throughout the pad 10, is most easily constructed, it also entraps
a relatively large quantity of air and thus, the pressure signals
may be somewhat attenuated. In FIG. 2, therefore, an embodiment of
the flexible pad 10 is disclosed where individual pockets or
fingers 32 of resilient material are individually enclosed within a
flexible non-porous material, and are spaced such that some portion
of the infant will always rest upon one or more of the fingers 32.
In this manner, the amount of entrained air is reduced and a less
attenuated pressure signal is realized.
Although the fingers 32 are shown in elongated form, they may also
be of other configurations, including spherically shaped
fluid-tight pockets.
Turning now to FIG. 3, there is shown, in block form, a schematic
of a typical electronic circuit 30 utilized in this invention. The
individual circuits shown are of generally conventional designs so
that only their overall function will be explained. As shown, the
circuit 30 is used wherein only one sensed movement is monitored,
such as breathing rate, however, a similar electronic circuit may
also be used where both breathing rate and heart rate movements are
sensed.
Briefly, the flexible pad 10, as previously explained, experiences
pressure fluctuations in response to the breathing rate of an
infant resting thereon and these pressure changes are transmitted
to the transducer 16. The transducer 16, in the preferred
embodiment is caused to change its capacitance in response to the
pressure variations received, and a detection circuit 32 is
provided in order to sense the capacitance changes and transmit the
changes in the form of an analog signal for amplification by the
amplifier 34.
This amplified analog signal may then be applied to a known circuit
such as a Schmitt trigger, where the analog signal is converted to
a digital signal by a preselected analog range.
The Schmitt trigger 36 is a generally known electrical circuit
which is adapted to tripper a digital pulse when an analog signal
of a predetermined signal amplitude is reached, and continue to
transmit the constant digital pulse until the analog signal
thereafter falls below a predetermined cut-off strength.
A respiration indicator 38 receives the digital signal from the
Schmitt trigger 36 and provides a visual monitoring read-out means
such as by a meter or digital read-out. At this point, therefore,
hospital personnel may have a continuous visual indication of the
breathing rate of the infant.
An apnea alarm 40 is also provided for an audible sound to warn of
severe apnea conditions and the alarm 40 receives a signal from the
Schmitt trigger 36 through a time delay 42. The purpose of the
intermediate time delay 42 is to introduce a predetermined delay
before an audible sound is triggered. The length of predetermined
delay is chosen in order that small stoppages in breathing rate,
i.e., less than 3 second delay do not sound the audible alarm, as
often times, the infant will experience short delays in breathing
followed immediately by a return to a normal breathing rate. The
time delay 42 serves to eliminate the short, or normal breathing
interruptions and only trigger the audible alarm where the
breathing rate has slowed or even ceased for a predetermined amount
of time, at which point, the attending hospital personnel are
warned of the severe apnea condition so that the necessary steps
may be taken. The circuit may also provide for silencing the alarm
once breathing has again resumed.
A conventional test circuit 44 may also be included in order to
afford continuous assurance that the alarm 40 is in proper working
condition.
There is thus provided an apnea alarm system for continuous
monitoring of the respiratory and heart rate of infants through a
resilient fluid-tight pad adapted to underlie the infant and which
transmits pressure variations to a highly sensitive pressure
transducer. Large pressure variations normally introduced through
gross body movements of the infant are automatically filtered out
of the pressure signal to the transducer while long continuous
pressure changes are stabilized at a desired zero metering point.
The pressure transducer thereafter undergoes a variation in
capacitance in response to the pressure variation, which is
detected, amplified, and applied to known visual as well as audible
monitoring systems.
* * * * *