U.S. patent application number 12/762563 was filed with the patent office on 2010-12-30 for apnea detector and system.
Invention is credited to Ori Elyada, Shaked Rahamim.
Application Number | 20100328075 12/762563 |
Document ID | / |
Family ID | 40328479 |
Filed Date | 2010-12-30 |
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United States Patent
Application |
20100328075 |
Kind Code |
A1 |
Rahamim; Shaked ; et
al. |
December 30, 2010 |
APNEA DETECTOR AND SYSTEM
Abstract
An apnea detector is disclosed. In some embodiments, a detector
unit in communication with a capacitive type sensor is adapted to
receive an electrical signal which is indicative of variable
capacitance resulting from movement of a subject and to emit an
alert signal when the received electrical signal is indicative of
symptoms of apnea. In one embodiment, a detector unit is in
communication with a curvature sensor adapted to detect a variable
curvature of a subject body surface resulting from breathing
patterns of a subject. The detector unit is attached to an article
of clothing of the subject. A monitoring system comprises a
detector unit for detecting one or more subject related parameters
of interest and for emitting acoustical information after
determining that a subject related parameter of interest has a
predetermined status, and a stationary unit disposed within an
audible range of the detector unit for receiving the emitted
acoustical information.
Inventors: |
Rahamim; Shaked; (Moshav
Netua, IL) ; Elyada; Ori; (Hod Hasharon, IL) |
Correspondence
Address: |
Marc Van Dyke
123 N.W. 13th Street, Suite 221
Boca Raton
FL
33432-1619
US
|
Family ID: |
40328479 |
Appl. No.: |
12/762563 |
Filed: |
April 19, 2010 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
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PCT/IL2008/001349 |
Oct 12, 2008 |
|
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12762563 |
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Current U.S.
Class: |
340/573.1 |
Current CPC
Class: |
A61B 5/6808 20130101;
A61B 2562/0261 20130101; A61F 5/56 20130101; A61B 5/7405 20130101;
A61B 5/1135 20130101; A61B 5/7282 20130101; A61B 5/113 20130101;
A61B 5/6804 20130101; A61B 5/0026 20130101; A61B 5/742 20130101;
A61B 5/0826 20130101; A61B 5/746 20130101; A61B 5/4818
20130101 |
Class at
Publication: |
340/573.1 |
International
Class: |
G08B 23/00 20060101
G08B023/00 |
Foreign Application Data
Date |
Code |
Application Number |
Oct 18, 2007 |
IL |
186768 |
Claims
1) A method of detecting apnea of a subject using one or more
capacitor plates, the method comprising at a time when at least one
of the capacitor plates is mechanically coupled to an article of
clothing worn by the subject: a) capacitively sensing a distance(s)
between: i) the mechanically coupled capacitor plate and; ii) a
surface of the subject's body, to generate a sensor-output
electrical signal; b) analyzing time variations in the
sensor-output electrical signal to determine if the time variations
are indicative of a symptom of apnea in the subject; and c)
generating an apnea alert signal that is contingent on the results
of the apnea determining.
2) The method of claim 1 wherein the capacitance sensing occurs
within a circuit comprising the following serially-connecting
circuit elements: i) a first of the capacitor plates; ii) the
subjects body; and iii) a second of the capacitor plates.
3) The method of claim 1 wherein there are at two capacitor plates
and each capacitor plate is attached to the article of clothing
such that the capacitor plates are next to each other separated by
an insulating portion of the article of clothing.
4) The method of claim 1 wherein at least one of the capacitor
plates is releasably attachable to the article of clothing.
5) The method of claim 1 wherein at least one of the capacitor
plates is embedded within the article of clothing.
6) Apparatus for detecting apnea of a subject comprising: a) a
capacitive displacement sensor including one or more capacitor
plates, the capacitor sensor configured, when deployed to an
article of clothing being worn by the subject, to capacitively
sense a distance between one or more of the capacitor plate(s) and
a surface of the subject's body to generate an output
capacitance-related electrical signal indicative of the sensed
distance; and b) a detector unit in communication with at least one
of the electrical sensors, the detector unit configured: i) to
receive the output capacitance-related electrical signal; ii) to
analyze time variations in the capacitance-related value to
determine if the time variations are indicative of a symptom of
apnea in the subject; and iii) contingent on the results of the
apnea determining, to generate an alert signal.
7) A system for detecting apnea of a subject, the system
comprising: a) a diaper; and b) a capacitance-sensor configured to
capacitively sense a distance(s) between: i) a diaper-associated
capacitor plate that is mechanically coupled to the diaper and that
is part of the capacitance sensor; and ii) a surface of the
subject's body when the diaper is worn by the subject, thereby
generating a capacitance output signal; c) a detector unit in
communication with at least one of the diaper-coupled electrical
sensors, the detector unit configured: to analyze time variations
the capacitance output signal to determine if the time variations
are indicative of a symptom of apnea in the subject; and d)
contingent on the results of the apnea determining, to generate an
alert signal.
8) A monitoring system, comprising (a) detector unit configured to
detect an indication of a condition requiring care by a parent,
guardian or medical professional; (b) a audio speaker for emitting
an audio alert signal contingent upon the detected indication of
condition requiring care by a parent, guardian or medical
professional; (c) a microphone in audible range of the audio
speaker configured to detect sound and to generate an electrical
signal descriptive of the detected sound; and (d) electrical
circuitry configured to analyze the electrical signal descriptive
of the detected sound and to determine if the electrical signal
descriptive of the detected sound matches the audio alert signal;
and (e) an alert signal-emitting unit configured, in response to
the results of the analysis by the electrical circuitry, and
contingent upon a positive matching to emit one or more additional
alert signals.
9) The system of claim 8 wherein: (i) the condition requiring care
by a parent, guardian or medical professional is apnea; and (ii)
the detected indication is a symptom of apnea.
10) The system of claim 8 wherein at least one of the additional
alert signals is a visual or audio or email or text-message or
radio or infra-red alert signal.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This patent application is a continuation-in-part of
PCT/IL2008/001349 filed on Oct. 12, 2008 and published as WO
2009/050702, and claims priority to Israel Patent Application
186768 filed on Oct. 18, 2007, which are all hereby incorporated in
their entirety by reference.
FIELD OF THE INVENTION
[0002] The present invention relates to the field of monitoring
systems. More particularly, the invention relates to an apnea
detector that is embedded in a diaper or otherwise attached to an
article of clothing.
BACKGROUND OF THE INVENTION
[0003] A constant concern of parents of a sleeping infant,
generally less than one year old, is the onset of sudden infant
death syndrome (SIDS). Parents usually inspect the breathing
patterns of their infant several times during a nighttime period to
determine whether there are signs of the onset of SIDS.
[0004] It would be desirable to provide a reliable and inexpensive
detector for infant apnea, which is one of the most recognizable
signs of SIDS. An infant who has ceased to breathe can be revived
only if a parent, who has been trained to provide first aid care,
is immediately alerted to such a life threatening condition.
[0005] Some adults are also prone to sleep apnea due to various
medical causes. It would be desirable to provide a reliable and
ergonomic detector for monitoring sleep apnea and for stimulating
the subject to awake when sleep apnea occurs.
[0006] Three types of prior art apnea detectors are known: [0007]
1) An apnea detector such as disclosed in U.S. Pat. No. 5,271,412,
WO 2005/074379, U.S. Pat. No. 4,146,885 and U.S. Pat. No. 5,684,460
is placed underneath the mattress of the infant, and a parent is
immediately alerted when apnea is detected. It is needless to say
that this type of detector is unable to detect apnea when the
infant is not sleeping, such as when playing, or when not sleeping
on his mattress. This type of detector is also relatively expensive
to manufacture. Another disadvantage of this type of apnea detector
is that the mattress is interposed between the infant and the
detector that senses the breathing pattern of the infant. The
received signal is therefore attenuated by the mattress material,
and its transmission is also delayed due to the gradual relaxation
of the spongy mattress material, causing a life threatening delay
during an apnea event. [0008] 2) One type of apnea detector, such
as disclosed in U.S. Pat. No. 5,454,376 or U.S. Pat. No. 5,241,300,
involves a wearing apparel having an elastic belt that extends
about the chest or abdomen of the infant. A strain gauge is secured
to the belt and detects breathing movement through the expansion
and contraction of the chest wall. Such a detector is uncomfortable
or even dangerous to the wearer, particularly during the nighttime
hours, due to the pressure exerted by the elastic belt, and
therefore cannot be used during an entire 24-hour period. Apnea
cannot be detected when the wearing apparel is being laundered.
Additional disadvantages of this type of detector are that the
detector is not suitable for different sized infants and that it is
not capable for detecting moisture in a diaper. [0009] U.S. Pat.
No. 5,295,490, U.S. Pat. No. 4,696,307, U.S. Pat. No. 4,989,612,
U.S. Pat. No. 5,107,855, and U.S. Pat. No. 5,400,012 disclose a
variation of this type of apnea detector in which belt means
encircling a portion of the body of a patient expands and contracts
in response to respiration of the patient. This belt means poses a
risk of entanglement and suffocation to the monitored infant.
[0010] 3) Another type of apnea detector, such as disclosed in GB
2261290, U.S. Pat. No. 3,782,368, U.S. Pat. No. 5,684,460, U.S.
Pat. No. 6,267,730 and WO 2005/011491, comprises a piezoelectric
element for detecting deflections caused by respiratory and heart
functions. A piezoelectric element is relatively expensive, and
therefore is not disposable. Also, a piezoelectric element is
fragile, and may be easily broken by the infant or by his parents,
therefore constituting an unreliable detector.
[0011] Other apnea detectors are disclosed in WO 02/34133, JP
9,187,431, U.S. Pat. No. 5,993,397 and U.S. Pat. No. 6,267,730.
[0012] U.S. Pat. No. 5,838,240 and U.S. Pat. No. 6,677,859 disclose
the use of a capacitive sensor for detecting moisture, such as in a
diaper. A capacitive sensor has not been used heretofore to detect
sleep apnea.
[0013] It is an object of the present invention to provide a
reliable and inexpensive detector for infant apnea.
[0014] It is an additional object of the present invention to
provide an infant apnea detector and system, which are operable
throughout a 24-hour period, even when the infant is awake and not
in a prone position.
[0015] It is an additional object of the present invention to
provide an infant apnea sensor that is embedded within a
diaper.
[0016] It is an additional object of the present invention to
provide an infant apnea sensor that is disposable.
[0017] It is an additional object of the present invention to
provide an infant apnea detector that is comfortable and safe to
the infant.
[0018] It is an additional object of the present invention to
provide an infant apnea detector that is difficult to be removed by
the infant from the diaper to which it is attached.
[0019] It is an additional object of the present invention to
provide an infant apnea detector and system that are also capable
of detecting wetness and other infant related parameters of
interest.
[0020] It is yet an additional object of the present invention to
provide an infant apnea detector system that can instantly alert a
parent upon detection of apnea.
[0021] It is yet an additional object of the present invention to
provide an infant apnea detector system that does not expose the
infant to close-proximity radio frequency (RF) radiation.
[0022] It is yet an additional object of the present invention to
provide an infant apnea detector and sensor that are not in direct
contact with the body of the infant.
[0023] Other objects and advantages of the invention will become
apparent as the description proceeds.
SUMMARY OF THE INVENTION
[0024] The present invention provides an apnea detector which
comprises a capacitive type sensor adapted to detect a variable
capacitance resulting from movement of a subject, such as the
breathing patterns of the subject, and a detector unit in
communication with said sensor for receiving an electrical signal
from said capacitive type sensor which is indicative of said
variable capacitance and for emitting an alert signal, such as by
alerting an attendant, when said received electrical signal is
indicative of symptoms of apnea, said detector unit being attached
to an article of clothing of the subject, such as a diaper.
[0025] As referred to herein, a "subject" is one who is being
monitored by means of an apnea detector, e.g. an adult subject or
an infant subject.
[0026] In one aspect, the detector unit is releasably attached to
an article of clothing of the subject.
[0027] In one aspect, the capacitive type sensor is adapted to
detect a variable capacitance between two serially connected
capacitor plates and a body surface of the subject.
[0028] In one aspect, the subject is an infant and the detector
unit is attached to a diaper.
[0029] In one aspect, the capacitive type sensor comprises a
conductive surface constituting a capacitor plate which is applied
to a suitable diaper surface, e.g. an inner face of a diaper outer
layer, such as being attached thereto, said sensor adapted to
detect a variable capacitance between said plate and a body surface
of the subject.
[0030] The variable capacitance is dependent upon an instantaneous
capacitance of diaper absorbent core material and an air gap
interposed between the plate and the subject body surface.
[0031] In one aspect, the conductive surface is applied to a
suitable diaper surface by conductive ink or hot foil stamping.
[0032] In one aspect, the conductive surface is attached to a
suitable diaper surface.
[0033] In one aspect, the sensor is capacitively coupled to the
detector unit.
[0034] In one aspect, the detector unit is in communication with
said sensor by means of electric contacts.
[0035] The detector unit preferably comprises a microcontroller, an
enunciator in communication with said microcontroller for emitting
acoustical information when symptoms of apnea are detected, a
battery, a flexible or rigid printed circuit board, means for
communicating with the capacitive type sensor, and a recessed
button for activating or deactivating said microcontroller or for
silencing an enunciated alarm signal.
[0036] The microcontroller receives and processes electrical
signals from the sensor, and determines by means of a firmware
algorithm whether symptoms of apnea are being exhibited. Subject
related parameters are stored in an event log module which is
associated with the microcontroller. Data is exchanged with the
microcontroller by means of an external data interface.
[0037] In one aspect, the means for communicating with the
capacitive type sensor comprises a coupling pad externally attached
to a detector unit casing underside and electrically connected with
the printed circuit board.
[0038] In one aspect, the detector unit comprises two or more
coupling pads, for communicating with two or more spaced capacitive
type sensors.
[0039] In one aspect, the detector unit further comprises an
optical indicator in communication with the microcontroller for
visually alerting an attendant when symptoms of apnea are detected
or for indicating a detector status.
[0040] In one aspect, the detector unit is also in communication
with one or more additional sensors adapted to detect infant
related parameters of interest, which are selected from the group
of urine detection, feces detection, subject heartbeat detection,
ambient temperature and humidity, illumination level, infant
locating transponder, body temperature, body activity, oxygen
saturation of arterial blood, and sleeping orientation of
infant.
[0041] In one aspect, the capacitive type sensor comprises two
spaced conductive surfaces constituting capacitor plates which are
applied to a substrate, said substrate being embedded within diaper
absorbent core material such that said two spaced conductive
surfaces face each other, said sensor adapted to detect a variable
capacitance between said two spaced conductive surfaces.
[0042] The present invention is also directed to an apnea detector
which comprises a curvature sensor adapted to detect a variable
curvature of a subject body surface resulting from breathing
patterns of a subject, and a detector unit in communication with
said sensor for receiving an electrical signal from said curvature
sensor which is indicative of said variable curvature and for
emitting an alert signal when said received electrical signal is
indicative of symptoms of apnea, said detector unit being attached
to an article of clothing.
[0043] The curvature sensor is selected from the group of a
resistive strain gauge, a flexion sensor, a piezoelectric
transducer, a sensor made of piezoresistive materials, a fiber
optic element for measuring bending or stretching by means of
optical refraction, diffraction, scattering, transmissivity, or
polarization, and a force-sensitive resistor.
[0044] In one aspect, the detector unit is releasably attached to
an article of clothing of the subject.
[0045] In one aspect, the subject is an infant and the detector
unit is attached to a diaper.
[0046] In one aspect, the detector unit comprises a
microcontroller, an enunciator in communication with said
microcontroller for emitting acoustical information when symptoms
of apnea are detected, a battery, a flexible or rigid printed
circuit board, means for communicating with the curvature sensor,
and a recessed button for activating or deactivating said
microcontroller or for silencing an enunciated alarm signal.
[0047] The present invention is also directed to a subject
monitoring system which comprises a detector unit for detecting one
or more subject related parameters of interest and for emitting
acoustical information after determining that a subject related
parameter of interest has a predetermined status, and a stationary
unit disposed within an audible range of said detector unit for
receiving said emitted acoustical information.
[0048] The stationary unit preferably comprises a microphone, a
microcontroller, means for filtering noise and tones that have a
frequency outside a predetermined frequency band and for
transmitting filtered signals to said stationary unit
microcontroller, and means for generating an alert signal when said
stationary unit microcontroller determines that the filtered
signals are indicative of a predetermined audio signal emitted by
the detector unit.
[0049] In one aspect, the predetermined audio signal emitted by the
detector unit is an acoustical signature.
[0050] In one aspect, the alert signal generated by the stationary
unit is a high-volume warning signal.
[0051] In one aspect, the alert signal is adapted to alert an
authorized attendant that a subject related parameter of interest
has a predetermined status.
[0052] In one aspect, the stationary unit further comprises a
transceiver, the alert signal being a wireless signal transmitted
by said stationary unit transceiver.
[0053] In one aspect, the stationary unit comprises means for
receiving, amplifying and emitting acoustical information
enunciated by the subject.
[0054] In one aspect, the stationary unit comprises a display in
communication with the stationary unit microcontroller for
outputting textual information indicative of the predetermined
subject status.
[0055] In one aspect, the stationary unit comprises one or more
optical indicators in communication with the stationary unit
microcontroller, illumination of each of said indicators being
indicative of generation of an alarm signal.
[0056] In one aspect, the stationary unit further comprises an
external data interface for exchanging data with the stationary
unit microcontroller.
[0057] In one embodiment, the system further comprises a portable
unit in communication with the stationary unit transceiver via a
communication network, said portable unit being accessible to the
authorized attendant and adapted to enunciate acoustical
information emitted by the stationary unit.
[0058] In one aspect, a subject related parameter of interest
detected by the detector unit is a characteristic breathing pattern
value (CBPV).
[0059] In one aspect, a capacitive type sensor in communication
with the detector unit transmits an electrical signal thereto which
is indicative of a variable capacitance CBPV.
[0060] In one aspect, the capacitive type sensor comprises a
conductive surface applied to a suitable diaper surface, said
sensor adapted to detect a variable capacitance between said
surface and a body surface of an infant.
[0061] In one aspect, a curvature sensor in communication with the
detector unit transmits an electrical signal thereto which is
indicative of a variable curvature CBPV representing a variable
curvature of a subject body surface.
[0062] In one embodiment, the system further comprises an override
unit in communication with the stationary unit transceiver and
connected to a set-top box of a home entertainment system, said
override unit adapted to interrupt the display of a program on said
home entertainment system and to display a predetermined video
frame thereon.
[0063] Some embodiments relate to an apnea detector, comprising a
capacitive type sensor adapted to detect a variable capacitance
resulting from movement of a subject, and a detector unit in
communication with said sensor for receiving an electrical signal
from said capacitive type sensor which is indicative of said
variable capacitance and for emitting an alert signal when said
received electrical signal is indicative of symptoms of apnea, said
detector unit being attached to an article of clothing of the
subject.
[0064] In some embodiments, the capacitive type sensor is adapted
to detect a variable capacitance resulting from breathing patterns
of the subject.
[0065] In some embodiments, the detector unit is releasably
attached to an article of clothing of the subject.
[0066] In some embodiments, the subject is an infant and the
detector unit is attached to a diaper.
[0067] In some embodiments, the capacitive type sensor comprises a
conductive surface constituting a capacitor plate which is applied
to a suitable diaper surface, said sensor adapted to detect a
variable capacitance between said plate and a body surface of the
infant.
[0068] In some embodiments, the variable capacitance is dependent
upon an instantaneous capacitance of diaper absorbent core material
and an air gap interposed between the plate and the infant body
surface.
[0069] In some embodiments, the suitable diaper surface is an inner
face of a diaper outer layer.
[0070] In some embodiments, the conductive surface is applied to a
suitable diaper surface by conductive ink or hot foil stamping.
[0071] In some embodiments, the conductive surface is attached to a
suitable diaper surface.
[0072] In some embodiments, the sensor is capacitively coupled to
the detector unit.
[0073] In some embodiments wherein the detector unit is in
communication with said sensor by means of electric contacts.
[0074] In some embodiments, the detector unit comprises a
microcontroller, an enunciator in communication with said
microcontroller for emitting acoustical information when symptoms
of apnea are detected, a battery, a flexible or rigid printed
circuit board, means for communicating with the capacitive type
sensor, and a recessed button for activating or deactivating said
microcontroller or for silencing an enunciated alarm signal.
[0075] In some embodiments, the means for communicating with the
capacitive type sensor comprises a coupling pad externally attached
to a detector unit casing underside and electrically connected with
the printed circuit board.
[0076] In some embodiments, the detector unit comprises two or more
coupling pads, for communicating with two or more spaced capacitive
type sensors.
[0077] In some embodiments, the detector unit further comprises an
optical indicator in communication with the microcontroller for
visually alerting an attendant when symptoms of apnea are detected
or for indicating a detector status.
[0078] In some embodiments, the detector unit is also in
communication with one or more additional sensors adapted to detect
subject related parameters of interest.
[0079] In some embodiments, wherein the subject related parameters
of interest are selected from the group of urine detection, feces
detection, heartbeat detection, ambient temperature and humidity,
illumination level, subject locating transponder, body temperature,
body activity, oxygen saturation of arterial blood, and sleeping
orientation of infant.
[0080] In some embodiments, the capacitive type sensor is adapted
to detect a variable capacitance between two serially connected
capacitor plates and a body surface of the subject.
[0081] In some embodiments, the capacitive type sensor comprises
two spaced conductive surfaces constituting capacitor plates which
are applied to a substrate, said substrate being embedded within
diaper absorbent core material such that said two spaced conductive
surfaces face each other, said sensor adapted to detect a variable
capacitance between said two spaced conductive surfaces.
[0082] Some embodiments of the present invention provide an apnea
detector, comprising a curvature sensor adapted to detect a
variable curvature of a subject body surface resulting from
breathing patterns of a subject, and a detector unit in
communication with said sensor for receiving an electrical signal
from said curvature sensor which is indicative of said variable
curvature and for emitting an alert signal when said received
electrical signal is indicative of symptoms of apnea, said detector
unit being attached to an article of clothing.
[0083] In some embodiments, the detector unit is releasably
attached to an article of clothing of the subject.
[0084] In some embodiments, the subject is an infant and the
detector unit is attached to a diaper.
[0085] In some embodiments, the curvature sensor is selected from
the group of a resistive strain gauge, a flexion sensor, a
piezoelectric transducer, a sensor made of piezoresistive
materials, a fiber optic element for measuring bending or
stretching by means of optical refraction, diffraction, scattering,
transmissivity, or polarization, and a force-sensitive
resistor.
[0086] Some embodiments of the present invention relate to a
monitoring system, comprising a detector unit for detecting one or
more subject related parameters of interest and for emitting
acoustical information after determining that a subject related
parameter of interest has a predetermined status, and a stationary
unit disposed within an audible range of said detector unit for
receiving said emitted acoustical information.
[0087] Some embodiments of the present invention relate to a
monitoring system, comprising (a) detector unit configured to
detect a presence of a symptom of apnea; (b) an audio speaker for
emitting an audio alert signal (i.e. for example, having
predetermined characteristics) contingent upon the detected
presence of a symptom of apnea; (c) a microphone in audible range
of the audio speaker configured to detect sound and to generate an
electrical signal descriptive of the detected sound; and (d)
electrical circuitry (i.e. including any combination of digital or
analog electrical hardware and/or software/executable computer
code--for example, including one or more microprocessors, volatile
and/or non-volatile memory, and/or executable code stored in
memory) configured to analyze the electrical signal descriptive of
the detected sound and to determine if the electrical signal
descriptive of the detected sound matches the audio alert signal;
and (e) an alert signal-emitting unit (e.g. including a speaker or
visual display or digital computer configured to sent an electronic
communication) configured, in response to the results of the
analysis by the electrical circuitry, and contingent upon a
positive matching (i.e. a determination that the electrical signal
descriptive of the detected sound from the microphone does match
the sound characteristics of the audio alert signal), to emit one
or more additional alert signals.
[0088] In one example, the additional alert signal is an additional
audio alert signal. In another example, the additional alert signal
may be visual alert signal. In yet another example, the additional
alert signal may be provided by an electronic communication such as
an email, a text message (e.g. an SMS), or a communication via a
packet switched and/or internet network. In yet another example,
the additional alert signal may be a radio signal or infra-red data
communication.
[0089] Some embodiments of the present invention relate to a
monitoring system, comprising (a) detector unit configured to
detect a indication of condition requiring care by a parent,
guardian or medical professional; (b) an audio speaker for emitting
an audio alert signal (i.e. for example, having predetermined
characteristics) contingent upon the detected indication of the
condition requiring care by a parent, guardian or medical
professional; (c) a microphone in audible range of the audio
speaker configured to detect sound and to generate an electrical
signal descriptive of the detected sound; and (d) electrical
circuitry (i.e. including any combination of digital or analog
electrical hardware and/or software/executable computer code--for
example, including one or more microprocessors, volatile and/or
non-volatile memory, and/or executable code stored in memory)
configured to analyze the electrical signal descriptive of the
detected sound and to determine if the electrical signal
descriptive of the detected sound matches the audio alert signal;
and (e) an alert signal-emitting unit (e.g. including a speaker or
visual display or digital computer configured to sent an electronic
communication) configured, in response to the results of the
analysis by the electrical circuitry, and contingent upon a
positive matching (i.e. a determination that the electrical signal
descriptive of the detected sound from the microphone does match
the sound characteristics of the audio alert signal), to emit one
or more additional alert signals.
[0090] Examples of conditions requiring care by a parent, guardian
or medical professional include a presence or urine or feces, apnea
and an abnormal body temperature.
[0091] In some embodiments, the stationary unit comprises a
microphone, a microcontroller, means for filtering noise and tones
that have a frequency outside a predetermined frequency band and
for transmitting filtered signals to said stationary unit
microcontroller, and means for generating an alert signal when said
stationary unit microcontroller determines that the filtered
signals are indicative of a predetermined audio signal emitted by
the detector unit.
[0092] In some embodiments, the predetermined audio signal emitted
by the detector unit is an acoustical signature.
[0093] In some embodiments, the alert signal generated by the
stationary unit is a high-volume warning signal.
[0094] In some embodiments, the stationary unit further comprises a
transceiver, the alert signal being a wireless signal transmitted
by said stationary unit transceiver.
[0095] In some embodiments, the stationary unit comprises means for
receiving, amplifying and emitting acoustical information
enunciated by the subject.
[0096] In some embodiments, the stationary unit comprises a display
in communication with the stationary unit microcontroller for
outputting textual information indicative of the predetermined
subject status.
[0097] In some embodiments, the stationary unit comprises one or
more optical indicators in communication with the stationary unit
microcontroller, illumination of each of said indicators being
indicative of generation of an alarm signal.
[0098] In some embodiments, the stationary unit further comprises
an external data interface for exchanging data with the stationary
unit microcontroller.
[0099] In some embodiments, the monitoring system further comprises
a portable unit in communication with the stationary unit
transceiver via a communication network, said portable unit being
accessible to the authorized attendant and adapted to enunciate
acoustical information emitted by the stationary unit.
[0100] In some embodiments, a subject related parameter of interest
detected by the detector unit is a characteristic breathing pattern
value (CBPV).
[0101] In some embodiments, a capacitive type sensor in
communication with the detector unit transmits an electrical signal
thereto which is indicative of a variable capacitance CBPV.
[0102] In some embodiments, the capacitive type sensor comprises a
conductive surface applied to a suitable diaper surface, said
sensor adapted to detect a variable capacitance between said
surface and a body surface of the infant.
[0103] In some embodiments, a curvature sensor in communication
with the detector unit transmits an electrical signal thereto which
is indicative of a variable curvature CBPV representing a variable
curvature of a subject body surface.
[0104] In some embodiments, the system comprises an override unit
in communication with the stationary unit transceiver and connected
to a set-top box of a home entertainment system, said override unit
adapted to interrupt the display of a program on said home
entertainment system.
[0105] In some embodiments, the override unit is adapted to display
a predetermined video frame on, or to enunciate voice information
by means of, the home entertainment system.
[0106] In some embodiments, the alert signal is adapted to alert an
authorized attendant that a subject related parameter of interest
has a predetermined status.
BRIEF DESCRIPTION OF THE DRAWINGS
[0107] In the drawings:
[0108] FIG. 1 is a schematic cross sectional view of a diaper
protectively attached to an infant body and having a pocket in
which a detector unit is retained;
[0109] FIG. 2 is a schematic illustration of a detector comprising
capacitive type sensors as it is attached to a diaper;
[0110] FIG. 3 is a schematic cross sectional view of a front
section of a diaper provided with the detector of FIG. 2, according
to one embodiment of the invention;
[0111] FIG. 4A is a schematic illustration showing the electrical
equivalent of each component of the detector of FIG. 3, including
the contribution of an infant body;
[0112] FIG. 4B is an electrical circuit corresponding to FIG.
4A;
[0113] FIGS. 5 and 6 illustrate a top view and a cross-sectional
view from the side, respectively, of a detector unit;
[0114] FIG. 7 is a schematic cross sectional view of a front
section of a diaper provided with the detector of FIG. 2, according
to another embodiment of the invention;
[0115] FIG. 8A is a schematic illustration showing the electrical
equivalent of each component of the detector of FIG. 7, including
the contribution of an infant body;
[0116] FIG. 8B is an electrical circuit corresponding to FIG.
8A;
[0117] FIG. 9A is a perspective view of another embodiment of a
capacitive type sensor;
[0118] FIG. 9B illustrates a cross-section of the capacitive type
sensor of FIG. 9A;
[0119] FIG. 10 is a schematic cross sectional view of a front
section of a diaper provided with the sensor of FIG. 9A;
[0120] FIG. 11 is a schematic cross sectional view of a front
section of a diaper provided with a curvature type sensor;
[0121] FIG. 12A is a schematic illustration of the detector unit of
FIG. 11;
[0122] FIG. 12B is a perspective view from the rear of the detector
unit of FIG. 12A;
[0123] FIG. 13A is a magnified view of the connection between a
curvature type sensor and a detector unit, according to one
embodiment of the invention;
[0124] FIG. 13B is a schematic cross sectional view of a detector
unit that is releasably attached to an article of clothing and
provided with a curvature type sensor;
[0125] FIG. 13C is a schematic cross sectional view of a detector
unit that is releasably attached to an article of clothing and
provided with both a curvature type sensor and a capacitive type
sensor;
[0126] FIGS. 14A-14E illustrate some embodiments related to a
curvature sensor;
[0127] FIG. 15 is a schematic illustration of an infant monitoring
system, according to one embodiment of the invention;
[0128] FIG. 16A is a block diagram of a detector unit, according to
one embodiment of the invention;
[0129] FIG. 16B is a flow diagram of steps performed by a detector
unit microcontroller to detect apnea;
[0130] FIG. 17 is a block diagram of a stationary unit, according
to one embodiment of the invention;
[0131] FIG. 18 is a block diagram of a portable unit, according to
one embodiment of the invention;
[0132] FIG. 19 is a schematic illustration of an infant monitoring
system, according to another embodiment of the invention; and
[0133] FIG. 20 is a block diagram of an override unit, according to
one embodiment of the invention.
DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS
[0134] The present invention is a novel detector and monitoring
system for apnea, and particularly for infant apnea. A detector
unit, which is attached to a clothing article of the subject, is in
communication with a sensor which may be ultra-thin, e.g. having a
thickness of less than 1 mm. Due to its thin size and
cost-effective manufacturing methods, such as being printed by
conductive ink, hot foil stamping, conductive polymer tape, and
vacuum metallization, the sensor is of low cost and can therefore
be sold as a disposable product. The detector unit is integrated
with a system, which will be described hereinafter, for instantly
alerting an attendant once apnea is detected. Even though the apnea
detector is in constant use, the subject is generally not exposed
to close-proximity radio frequency radiation.
[0135] When the subject is an infant, a detector unit is embedded
in, or otherwise attached to, a diaper, and due to its ergonomic
configuration by which substantially no discomfort is caused to the
infant, the detector unit may be in constant use throughout a
24-hour period, even when the infant is awake and not in a prone
position. Since the detector is adapted to detect the breathing
patterns of an infant who is distant from his bed or home, the
onset of apnea conditions in addition to sudden infant death
syndrome (SIDS), such as suffocation, can be advantageously
determined.
[0136] FIGS. 1-10 illustrate one embodiment of the invention
wherein the sensor is a capacitive type sensor which is adapted to
measure a variable capacitance, for example between a plate of the
sensor and a body surface of the infant. As the infant inhales and
exhales, the thickness of an air gap between the diaper and the
body surface of the infant periodically changes, and therefore the
sensed capacitance correspondingly changes, indicating that the
infant has a normal breathing pattern.
[0137] As schematically shown in FIG. 1, diaper 10 comprised of a
front section 2 and a rear section 5 is formed with a pocket 8 in
which the detector is retained. When diaper 10 is protectively
attached to infant body 12, the internal organs of which are not
illustrated, front section 2 and rear section 5 of diaper 10 are
connected by means of adhesive strips 7 and variable air gap 14
exists between diaper 10 and infant body 12. A change in the
thickness of air gap 14 is generally caused by the expansion and
contraction of the chest wall, and is also caused by the
compression of front section 2 of diaper 10. Sensors 16 and 17
retained in front section 2 detect the expansion and contraction of
the chest wall.
[0138] FIG. 2 schematically illustrates a detector generally
designated by numeral 6, which comprises apnea detector unit 20A
and sensors 16 and 17. Detector unit 20A is retained within pocket
8 of diaper 10 and secured thereto by means of adhesive tab 13.
Apnea detector unit 20A is interposed between, and in electrical
communication with, two conductive surfaces 16 and 17 constituting
capacitor plates, which are printed preferably, but not
limitatively, by conductive ink or hot foil stamping, as well known
to those skilled in the art. Detector unit 20A may also be in
communication with one or more additional sensors 19 that are
adapted to detect infant related parameters of interest, such as
urine detection, feces detection, infant heartbeat detection,
ambient temperature and humidity, illumination level, body
temperature, body activity, infant locating transponder, and
sleeping orientation of infant. Detector unit 20A may also be in
communication with an electronic device, such as an audio
monitoring device, and may be provided with means for logging
infant activity events. Plates 16 and 17, additional sensors 19,
and monitoring equipment are connected to detector 20A by means of
corresponding electrical contacts 21 provided in the casing of
detector 20A, or, alternatively by means of capacitive coupling
through a layer of diaper 10, as will be described hereinbelow.
Pocket 8 is preferably formed with one or more holes 22. A hole 22
may be used, for example, to enhance acoustic conductance of a
beeper, to facilitate access to a deactivation button, or to
improve the viewability of light emitting diode (LED)
indicators.
[0139] FIG. 3 illustrates front section 2 of a diaper, which
comprises outer layer 3, absorbent core 9, and inner layer 18,
showing the connection in magnified cross sectional view between
plates 16 and 17 and detector unit 20A. Detector unit 20A is placed
within pocket 8A, which is welded or bonded to the exterior face of
the waterproof outer layer 3 of the diaper. Plates 16 and 17, which
are printed on, or attached to, the inner face of outer layer 3 and
in contact with absorbent core 9 of the diaper, are capacitively
coupled to detector unit 20A by means of coupling pads 23A-B
printed on the inner face of diaper outer layer 3 (hereinafter
"diaper side coupling pads") and coupling pads 24-B attached to the
casing of detector unit 20A (hereinafter "detector side coupling
pads"). Conductor 26 connects plate 16 and diaper side coupling pad
23A, and conductor 27 connects plate 17 and diaper side coupling
pad 23B.
[0140] FIGS. 4A-B schematically illustrate the electrical
equivalent of the circuit 35 defined by the apparatus of this
embodiment. As shown, capacitance 31 and capacitance 32 are the
variable capacitances between plates 16 and 17, respectively, and
infant body 12, wherein the variable capacitance is dependent on
the instantaneous thickness of absorbent core 9 of the diaper and
of air gap 14 (FIG. 3). Resistance 34 is the equivalent resistance
of infant body 12. Capacitance 36 is the fixed capacitance between
coupling pads 23A and 24A, while capacitance 37 is the fixed
capacitance between coupling pads 23B and 24B. Equivalent circuit
35 comprises detector 20A, fixed capacitance 36, variable
capacitance 31, resistance 34, variable capacitance 32, and fixed
capacitance 37, which are all connected in series.
[0141] As well known, the combined capacitance of capacitors in
series is the reciprocal of the sum of the reciprocal of the
capacitances. In order to be able to accurately detect and transmit
the instantaneous capacitance between a capacitor plate and the
infant body, which is indicative of whether the infant has normal
breathing patterns, the value of the fixed capacitance therefore is
preferably, but not necessarily, greater than the value of the
variable capacitance, which is serially connected therewith. The
equivalent capacitance of circuit 37 is therefore dominated by
variable capacitances 31 and 32, while resistance 34 does not
considerably affect the capacitance measurement. Detector unit 20A
is adapted to sense the total equivalent capacitance of circuit 37,
and by comparing the total equivalent capacitance over time, i.e.
with respect to several breaths or with respect to previous
measurements, it is able to determine whether the infant has normal
breathing patterns. By comparing the total equivalent capacitance
with a nominal value, which is generally empirically measured,
detector 20A may also advantageously determine whether air gap 14
is of an average value, much smaller than the nominal value
indicating that the diaper is loosely attached to the infant, or
much greater than the nominal value indicating the diaper is
attached to the infant in an excessively tight manner, whereupon a
parent is alerted.
[0142] In order to allow for manufacturing tolerances and
mechanical movement of the detector within the pocket, it is
desirable that diaper side coupling pads 23A-B be of a larger size
than the corresponding detector side coupling pads 24A-B, so that
the entire area of a diaper side coupling pad overlap the
corresponding detector side coupling pad, so that the coupling
capacitance between a diaper side coupling pad and the
corresponding detector side coupling pad remains constantly
high.
[0143] FIGS. 5 and 6 illustrate a top view and a cross-sectional
view from the side, respectively, of a detector unit 20A. The
components of detector 20A are mounted within casing 41, which may
be made of plastic material, while being sealed and water
resistant. Casing 41 is ergonomically configured with a thin and
curvilinear structure that is shaped without any sharp protrusions,
so that when retained in pocket 8A (FIG. 3), casing 41 does not
cause any discomfort to the infant when a portion of the infant
body is pressed thereagainst. Arcuate side portions 38 of casing
41, which may contact pocket 8A (FIG. 3) by means of opposed side
recessed portions 54 and 55 for engaging complementary protrusions
of the pocket, are integrally formed with underside 39 and with
upper portion 42 thereof.
[0144] Detector unit 20A comprises a microcontroller 43, a recessed
button 45 for activating or deactivating microcontroller 43, for
silencing an enunciated alarm signal, or for any other desired user
input, upon depression of an overlying region 46 of upper casing
portion 42, an enunciator 47, e.g. of the piezoelectric or
electromagnetic type, for audibly alerting a parent when symptoms
of apnea are detected and placed beneath a thin layer 48 of upper
casing portion 42 to minimize the attenuation of the alarm signal,
a battery 49, e.g. of the CR2032 coin cell type, a flexible or
rigid printed circuit board 51 electrically connected to
microcontroller 43, button 45, enunciator 47, and battery 49, and
coupling pads 24A-B externally attached to underside 39. A portion
of coupling pads 24A-B protrudes through underside 39 and is
connected with conductors 53A-B, respectively, which in turn are
electrically connected with printed circuit board 51. One or more
light, LED, or any other suitable optical indicator, in
communication with microcontroller 43 may be used to visually alert
a parent if casing 41 is not opaque. Contacts 57A-B for connecting
one or more additional sensors are also connected to underside
39.
[0145] FIG. 7 illustrates front section 2 of a diaper, which
comprises outer layer 3, absorbent core 9, and inner layer 18,
showing the connection in magnified cross sectional view between
plates 16 and 17 and detector unit 20A. Detector unit 20A is placed
within pocket 8B, which is welded or bonded to the inner face of
the waterproof outer layer 3 of the diaper. Although pocket 8B is
embedded within absorbent core 9, it can be easily accessed by
means of a suitable incision effected in diaper outer layer 3.
[0146] In this embodiment, detector unit 20A is directly connected
to sensor plates 16 and 17. Detector side contacts 58A-B attached
to the exterior face of casing underside 39 (FIG. 6) of detector
20A are electrically connected to diaper side contacts 59A-B,
respectively. Contacts 59A-B in turn are electrically connected to
plates 17 and 16, respectively by means of conductors 61A-B,
respectively, which are attached to the inner face of outer layer
3, extending from a diaper side contact to a corresponding plate.
The electrical connection between a detector side contact and a
corresponding diaper side contact is sustained by minimizing the
clearance between the walls of pocket 8B and the casing of detector
20A, so that the walls of pocket 8B will apply a sufficiently high
outwardly directed force, i.e. towards outer layer 3, to detector
unit 20A, and by providing a suitable texture and/or structure to
the contacts 58A-B and 59A-B.
[0147] FIGS. 8A-B schematically illustrate the electrical
equivalent of the circuit 67 defined by the apparatus of this
embodiment. As shown, capacitance 31 and capacitance 32 are the
variable capacitances between plates 16 and 17, respectively, and
infant body 12, wherein the variable capacitance is dependent on
the instantaneous thickness of absorbent core 9 of the diaper and
of air gap 14 (FIG. 3). Detector unit 20A is connected to
capacitance 31 by means of contacts 58B and 59B, and is connected
to capacitance 32 by means of contacts 58A and 59A. Thus equivalent
circuit 67 comprises detector unit 20A, variable capacitance 31,
resistance 34, and variable capacitance 32, which are all connected
in series. The resistance of infant body 12 and contacts 58A-B and
59A-B, which are connected in series, do not significantly affect
the measurement of the equivalent capacitance.
[0148] FIG. 9A illustrates another embodiment of a capacitive type
apnea sensor, which is designated by numeral 70. In the capacitive
type sensor of FIG. 9A, the capacitance between capacitor plates is
sensed, and an apnea alarm responds to variations of the sensed
capacitance.
[0149] In some embodiments, sensor 70, which is shown partially
folded, comprises a flexible substrate 72, e.g. made of paper, card
or thin plastic, and two spaced rectangular conductive elements 73
and 76, which constitute capacitor plates, applied to the same face
of substrate 72 by conductive ink, hot foil stamping, bonding, or
vacuum metallization. Substrate 72 is folded to define an inner
portion 65 that includes element 73, an outer portion 69 that
includes element 76, and a crease 67 interposed between inner
portion 65 and outer portion 69.
[0150] Conductive strip 74 extends from conductive element 73 to
outer portion 69 without contacting element 76, and aperture 75 is
bored at the terminal end of strip 74. Curved conductive appendage
77 extends from element 76, and aperture 78 is bored therein. An
electrically insulating layer may be applied to conductive elements
73 and 76, strip 74, and appendage 77.
[0151] It will be appreciated that substrate 72 may be folded in
any other desired fashion, so that in such a configuration
conductive elements 73 and 76 may be applied to different faces of
substrate 72.
[0152] In some embodiment, it is possible to deploy the capacitor
plates 73 and 76 so that mechanical force transferred from the
surface of the patient during his/her breathing cycle cyclically
modifies a distance between plates 73 and 76. For the present
disclosure, a "transfer of mechanical force" excludes the case of
hydraulic and/or pneumatic means. In this example, surface of the
subject's body moves up and down during breathing, increasing and
decreasing upward pressure from the body surface to one or both of
the plates. This increasing and decreasing outward pressure from
the surface/skin of the subject may mechanically move one or more
`capacitive plates` closer together or farther apart, cyclically
modifying the capacitance between the plates according to the
breathing cycle. In some embodiments, it is possible to monitor the
temporal variance of the capacitance, and when the capacitance
between the capacitor plates or its temporal variance indicates a
symptom of apnea, to generate an alarm signal.
[0153] In one non-limiting example, at least a portion of an
article clothing (for example, a diaper) is located between or
"sandwiched between" the plates 73 and 76. In another example, some
sort of sponge is located between or "sandwiched between" the
plates 73 and 76. In yet another example, there is no `material`
between plates 73 and 76 other than air.
[0154] It is appreciated that the capacitor "plates" 73 and 76 are
not required to be flat and/or rectangular as shown in the
figure.
[0155] Some embodiments of the present invention relate to a method
of detecting apnea that is carried out at a time when capacitive
plates 73 and 76 are mechanically coupled and/or deployed to an
article of clothing worn by the subject (e.g. including but not
limited to a diaper). The method comprises the steps of: (a) for
first 73 and second 76 capacitive plates, each capacitive plate
being deployed to the article of clothing, sensing a capacitance
between the first and second capacitive plates; (b) analyzing time
variations of one or more of the sensor-output electrical signals
to determine if the time variations are indicative of a symptom of
apnea in the subject; and (c) generating an apnea alert signal that
is contingent on the results of the apnea determining.
[0156] FIG. 9B illustrates a cross-section of the capacitive type
sensor of FIG. 9A. As illustrated in FIG. 9B, the outward force
from the subject's breathing 260 may cyclically increase and
decrease in value (even reach a value of zero or a negative value).
This force from the subject's body (e.g. the surface or skin) is
transferred mechanically (i.e. see the arrow of 260) without any
need for pneumatic or hydraulic force-transfer means to one or both
of the capacitive plates 73, 76. In some embodiments, an additional
inward force 261 in reaction to the outward force 260 may also act
upon (i.e. mechanically without any need for pneumatic or hydraulic
force-transfer means) one or both plates 73, 76 thereby influencing
the capacitance between the plates which may be sensed and used to
apnea detecting.
[0157] As shown in FIG. 10, sensor 70 is embedded within absorbent
core 9 of a diaper in such a way that inner portion 65 and outer
portion 69 face each other. Outer portion 69 of the substrate may
be attached to outer layer 3 of the diaper and inner portion 65 of
the substrate may be attached to inner layer 18 of the diaper.
Detector unit 20B, in which are housed the same components as
detector unit 20A (FIG. 6), is coupled to sensor 70 such that it is
mounted externally to diaper outer layer 3. Detector unit 20B may
be coupled to sensor 70 by means of metallic rivets (not shown) in
engagement with apertures 75 and 78 (FIG. 9A) and in electrical
communication with circuit board 51 (FIG. 6). The rivets also
facilitate attachment of outer portion 69 of the substrate to outer
layer 3 of the diaper. Alternatively, the underside of the casing
of detector unit 20B may be provided with a backing 62 made of
Velcro.RTM. (hook and loop fasteners), which is adapted to be
coupled with complementary material 64 attached to the outer face
of diaper outer layer 3, and with electromechanical snap connectors
63A-B, which are adapted to engage with complementary terminals,
respectively, attached to outer layer 3 and in electrical
communication with a corresponding conductive element. If so
desired, the Velcro.RTM. material may be afforded conductive
properties. It will be appreciated that a detector unit 20A
provided with capacitive coupling pads, as illustrated in FIG. 6,
may also be employed.
[0158] As the infant inhales and exhales, the thickness of air gap
14 diaper inner layer 14 and infant body 14 periodically changes,
causing substrate inner portion 65 to be displaced and the
absorbent core material to be compressed. The displacement of
substrate inner portion 65 with respect to the substantially
stationary substrate outer portion 69 results in a varying
capacitance corresponding to that of the absorbent core material
interposed between conductive elements 73 and 76, indicating that
the infant has a normal breathing pattern.
[0159] With reference to FIG. 9A, an additional sensor, such as a
urine and/or feces detector, in addition to apnea sensor 70, can be
applied to substrate 72. The additional sensor comprises electrodes
81 and 82, which are also applied to substrate 72 and bored with
apertures 83 and 84, respectively, in electrical communication with
the detector. Apertures 83 and 84 may be arranged such that they
are collinear with apertures 75 and 78 of the conductive elements.
To enhance the sensing of bodily excretions, substrate 72 may be
produced from material having superior liquid-wicking and
electrical conduction properties. Electrodes 81 and 82 may be
applied to substrate inner portion 65 as shown, or alternatively,
to substrate outer portion 69.
[0160] FIGS. 11-14 illustrate another embodiment of the invention
wherein the apnea sensor is adapted to measure periodic changes in
the curvature of a body surface of an infant. Periodic changes in
the curvature of the body surface are indicative that the infant
has normal breathing patterns.
[0161] As shown in the example of FIG. 11, sensor 95 is adapted to
measure the curvature C of body surface 92 of an infant. Sensor 95
is in communication with detector unit 20C, which is shown to be
attached to front section 2 of a diaper by means of a backing 62
made of Velcro.RTM. and adhesive strips 7. Sensor 95 may include a
resistive strain gauge, a flexion sensor, a piezoelectric
transducer, a sensor including one or more of piezoresistive
materials, a fiber optic element for measuring bending or
stretching by means of optical refraction, diffraction, scattering,
transmissivity, or polarization, a force-sensitive resistor, or any
other sensor well known to those skilled in the art. As will be
discussed below, the output of curvature sensor 95 is significantly
influenced and/or governed primarily by perpendicular forces on
sensor 95. FIG. 12A illustrates a schematic, cross sectional view
of detector unit 20C, and FIG. 12B illustrates a perspective view
from the rear of detector unit 20C.
[0162] The particular example of FIGS. 12A-12B relate to a `hybrid
detector` that include both (i) elements for detecting capacitance
(e.g. 105A, 105B) (ii) as well as a curvature sensor (for example,
which outputs a resistance parameter that is governed by a measured
curvature). In experiments conducted by the present inventors, it
has been found that the use of the multiple sensors (i.e.
capacitance and curvature sensors) may produce a device that is
more accurate than a device that includes only one type of sensors.
Nevertheless, it is appreciated that there is no requirement for
both types of sensors to be present, and some embodiments relate to
the case where a curvature sensors is provided without any required
capacitance sensors (or vice-versa--i.e. where the capacitance
sensor is provided without any required curvature sensor).
[0163] For the example of FIGS. 12A-12B, curvilinear housing 102 of
detector unit 20C is configured with a winglike bilateral symmetry,
and is provided with an elevated central portion 107 and relative
thin extremities 108A-B. Microcontroller 43, recessed button 45,
enunciator, 47, battery 49, and flexible circuit board 101 are
housed within central portion 107. The winglike configuration of
housing 102 advantageously increases the engagement area of
Velcro.RTM. backing 62, and furthermore, enables attachment to
extremities 108A-B by adhesive strips 7, as shown in FIG. 11. The
winglike configuration of housing 102 also provides flexibility in
terms of sensor selection. Flexible capacitive plates 105A-B of
increased area can be embedded within, or printed on an inner
surface 106 of, extremities 108A-B, respectively, for enhanced
sensitivity. In the particular example of FIG. 12A, a curvature
sensor such as a resistive strain gauge 95A may be deployed within
central portion 107, such as printed on flexible circuit board 101
as shown. Alternatively, resistive strain gauges may be housed
within extremities 108A-B, respectively. Velcro.RTM. backing 62 may
be applied to the entire inner surface 106, or a portion
thereof.
[0164] It is appreciated that strain gauges may measure a force or
stress caused by `pulling` on the ends of strain gauge 95A (i.e.
parallel tensile stress)--therefore, the strain gauge 95A is not,
by itself a curvature sensor 95 which measures `perpendicular
forces` that are perpendicular to a tangent 293 around the
circumference of the patient and/or perpendicular to a "flat
surface" the substantially flat curvature sensor 95. Therefore, in
the example of FIG. 12A, one or more mechanical elements may be
provided to `translate` radially-outward force that is
substantially perpendicular to a length of the strain gauge and/or
perpendicular to a vector connecting stretchable ends 89A, 89B into
a tension and/or compression that is substantially parallel to
tangent 293.
[0165] In one example, strain gauge is embedded within central
portion 107 which is semi-rigid or substantially rigid (but not
completely rigid). In this example, because strain gauge 95A is
embedded within the semi-rigid or substantially rigid material,
radially outward force caused by the subject's breathing that is
perpendicular to 293 and/or perpendicular to the substantially flat
surface of strain gauge 95A is `diverted around` or `transferred
to` ends 89A and 89B. Thus, the semi-rigid or substantially rigid
material converted a force perpendicular to the substantially flat
surface to one which `pulls the ends` of this substantially flat
surface and can then be measured by strain gauge 95A--thus,
strictly speaking, strain gauge 95A is not by itself a curvature
sensor 95 but rather is a part of a curvature sensor 95.
[0166] In yet another example, an end 89A of strain gauge is
attached to "flexible" printed circuit board 101 (which is not that
`flexible` and which, in reality, is known to be at least
semi-rigid), and flexible printed circuit board 101 plays a roll in
converting the outward force perpendicular to tangential axis 293
into force along tangential axis 293--for example, according to a
mechanism similar to the mechanism explained below with reference
to FIG. 14E.
[0167] In order to support connectivity to other disposable sensors
such as urine detection electrodes, selected regions of Velcro.RTM.
backing 62 may have electrically conductive properties.
Alternatively, adhesive strips 7 (FIG. 11) may be conductive, so as
to connect a sensor to external contacts provided on housing
102.
[0168] In FIG. 13A, the curvature sensor is shown to be a flexion
sensor 95B, such as one manufactured by Flexpoint Sensor Systems,
Inc., Draper, Utah, USA, which is adapted to convert the bending of
a substrate into a variable resistance. Detector unit 20D is
retained within pocket 8A attached to the outer face of diaper
outer layer 3, and is in communication with flexion sensor 95B by
means of conductor 91 connected to flexion sensor 95B and contacts
93A-B of detector unit 20D, which are in communication with
conductor 91. By mounting, or directly printing, flexion sensor 95B
on a semi-flexible insert 97 attached to the inner face of diaper
outer layer 3, any change in the curvature of the diaper, such as a
result of breathing movement, can be sensed as a periodic change in
resistance.
[0169] FIG. 13B illustrates a detector unit 20D for determining
when an adult subject is suffering from apnea. Detector unit 20D
comprises curvature sensor 95, e.g. sensor 95A of FIG. 12A or
sensor 95B of FIG. 13A, and is adapted to measure the curvature of
body surface 94 of an adult 96. Housing 102A of detector unit 20D
may be configured with a winglike bilateral symmetry as shown, or
with any other suitable configuration. Housing 102A may be
releasably attached to an article of clothing 111, such as an upper
portion of pants, pajamas or underwear, or a lower portion of a
shirt, by means of clips 110A and 110B attached to inner surface
106A of housing 102A. Alternatively, housing 102A may be releasably
attached to article of clothing 111 by means of flexible magnets
109A-B, e.g. polymer magnets, of opposite polarity. Magnet 109A is
placed between clothing article 111 and body surface 94, and magnet
109B is attached to, or integral with, inner surface 106A, so that
magnets 109A and 109B will be coupled together while clothing
article 111 is positioned therebetween to ensure that body surface
94 will be spaced less than a predetermined maximum distance from
housing inner surface 106A.
[0170] In FIG. 13C, adult apnea detector unit 20E configured with
housing 102A comprises both curvature sensor 95 and flexible
capacitive plates 105A-B. It will be appreciated that an adult
apnea detector unit may be provided solely with a capacitive type
sensor. Similarly, an adult apnea detector may be employed in
conjunction with any of the embodiments described hereinabove.
[0171] In FIG. 14A, curvature sensor may be deployed together with
semi-rigid or substantially rigid (but not completely rigid)
substrate 264 (for example, made of semi-rigid or substantially
rigid plastic). In the example of FIG. 14A, curvature sensor 95 is
"above" the semi-rigid or substantially rigid (but not completely
rigid) substrate 264 (or farther from the skin)--alternatively,
curvature sensor 95 may be "below" the semi-rigid or substantially
rigid (but not completely rigid) substrate 264.
[0172] As it shown in FIG. 14A, the length of the substrate 264
along tangential axis 14A may exceed the length of curvature
sensor--for example, by a factor of at least 20% or 30% or 40% or
50% or 75% or 100% or any number. Because substrate 264 is not
completely rigid, outward force 262 due to the subject's breathing
will deform substrate 264 and modify the curvature of substrate 264
(for example, at least in part due to reactive forces 263A, 263B).
Because substrate 264 is not flexible but is semi-rigid or
substantially, forces perpendicular to a substantially flat surface
of substrate 264 (i.e. even at locations within substrate 264 that
are `far` from curvature sensor 95) may cause a force perpendicular
to a substantially flat surface of curvature sensor 95 to deform
curvature sensor. Thus, the semi-rigid or substantially rigid
substrate 264 may be said to amplify the signal of force 262.
[0173] In some embodiments, the electrical resistance parameter
output by curvature sensor 95 varies as a function of time
according to the breathing cycle. There is a certain magnitude in
change of the electrical resistance parameter as the curvature
sensor 95 senses a cyclical change in curvature. In some
embodiments, (for example, related to a curvature sensor 95 that
whose length (e.g. along tangential axis 293) is at most 200% or
150% or 100% or 85% or 65% or 50% of a length (e.g. along
tangential axis 293) of semi-rigid or substantially rigid substrate
264), the presence of the semirigid or substantially rigid
substrate 264 (i.e. deployed so that substrate 264 is between the
subject's skin and curvature sensor 95 as shown in FIG. 14A or
deployed so that curvature sensor 95 is between the subject's skin
and substrate 264) significantly contributes to variations in the
output electrical resistance parameter outputted by curvature
sensor. Thus, in some embodiments, the absence of the semirigid or
substantially rigid substrate 264 causes much smaller output
resistance parameter variations output by curvature sensor 95 (i.e.
output resistance parameter variations whose magnitude is at most
50%, or at most 40%, or at most 10% of a magnitude in the presence
of semirigid or substantially rigid substrate 264 during the baby's
breathing cycle.
[0174] As shown in FIG. 14B, in some embodiments, sensor 95 has a
`length` of curvature sensor 95 along a circumference of the
subject (i.e. along tangential axis 293) and perpendicular to an
elongate axis 291 of the subject. In some embodiments, this
`length` is less than 50% or 45% or 40% or 35% or 30% of a
circumference of 272 the subject at the location of curvature
sensor 95. In some embodiments, the length of curvature sensor 95
(i.e. along an elongate axis and/or axis 293) is at most 25 cm.
[0175] FIGS. 14C-14D relate to the definitions `local outward
force` in contrast to any `outward force` which is caused by the
breathing of the subject. The `local outward force` relative to
curvature sensor 95 is outward force at the location where the
curvature sensor is deployed above the surface of the subject.
Thus, in FIG. 14C (i.e. where curvature sensor 95 is deployed above
the article of clothing AOC 295) and in FIG. 14D (i.e. where
curvature sensor 95 is deployed below the article of clothing AOC
295) the forces identified by 999A-999E are `local outward forces`
along a vector which intersects a surface of the curvature sensor
95. In contrast, forces identified by 999F-999N are non-local. In
some embodiments, the variations of the electrical resistance
parameter which is output by curvature sensor during the breathing
cycle are governed primarily by variations of the local outward
forces during the breathing cycle--for example, which reach a
maximum when the subject is inhaling and decrease when the subject
is exhaling. In some embodiments, time variations in the sensed
`local outward forces` contribute at least 30% or 50% or 70% or 90%
to the total variations of the output resistance parameter during
the breathing cycle.
[0176] FIG. 14E relates to yet another example where curvature
sensor 95 may include a strain gauge 95A. Thus, in FIG. 14E,
element 264 is a semi-flexible or substantially flexible substrate
264, force 262 is an outward force from the subject due to
breathing, forces 263A and 263B are reactionary inward forces from
the semi-flexible substrate in reaction to force 262. The inward
forces 263A, 263B cause the substrate 264 to bend and modify its
radius of curvature, inducing tension 266 or compression 267 in a
direction substantially parallel to axis 293. This tension or
compression may be measured by strain gauge 95A which is a part of
curvature sensor 95. Without the presence of a semi-flexible or
substantially flexible substrate 264 as described above, strain
gauge 95A by itself is not a curvature sensor 95.
[0177] In some embodiments, when curvature sensor 95 is subjected
to a change in curvature from flat radius of curvature of 20 cm,
the resistance parameter output by curvature sensor 95 changes by
larger a percentage than when subjected to a change in tensile or
longitudinal stress (e.g. along axis 293 or along an axis
substantially parallel to a substantially flat surface of curvature
sensor 95) from relaxed to a tensile force of 10 N.
[0178] In some embodiments, curvature sensor 95 is not part of a
`closed mechanical loop` which closes upon itself to provide an
inward force throughout a majority or a substantial majority (i.e.
at least 60% or 70% or 80% or 90% or 95% of a circumference 272 of
the subject) in response to an outward force of breathing. Instead,
curvature sensor 95 may be part of a flexible article of clothing
and therefore does not hinder breathing.
[0179] FIG. 15 illustrates a monitoring system generally designated
by numeral 120, according to one embodiment of the present
invention. System 120 comprises detector unit 20, stationary unit
130 in communication with detector unit 20, and portable unit 150
accessible to a parent or to any other authorized attendant and in
communication with stationary unit 130. Detector unit 20 is
embedded in diaper 10, or otherwise attached to an article of
clothing, preferably in communication with an apnea sensor, as
described hereinabove, and optionally with one or more additional
sensors adapted to detect infant related parameters of interest,
and may be configured as detector unit 20A (FIG. 6), 20B (FIG. 10),
20C (FIGS. 11-12), 20D (FIG. 13), or any other desired
configuration.
[0180] As opposed to prior art detector units that are embedded or
otherwise attached to a diaper and that remotely transmit sensed
data by means of radio frequency (RF) waves, thereby exposing the
infant to harmful levels of RF radiation, detector unit 20
advantageously transmits acoustical information to stationary unit
130. Detector unit 20 emits acoustical information A after
determining that a subject related parameter of interest has a
predetermined status, as sensed by one of the sensors in
communication therewith. Stationary unit 130, which is supported by
a selected structure, such as a bed post or a table, and is
disposed within an audible range of detector unit 20, receives
emitted acoustical information A and determines that it is
indicative of a predetermined subject parameter status. A wireless
signal S indicative of the determined subject parameter status is
then transmitted to portable unit 150 via any suitable data
network, so that the attendant will take corrective actions. A
subject parameter status may be that a diaper is overly wet or
overly tight, or that the detector unit battery is drained. When
the determined subject parameter status requires immediate
attention, such as when symptoms of apnea are detected, stationary
unit 130 enunciates a warning signal W significantly louder than
acoustical information A and displays textual information on
display 122 and/or LEDs 124 become illuminated, and the authorized
attendant is immediately alerted by means of portable unit 150. If
so desired, detector unit 20 may be any dedicated unit for
detecting a subject related parameter of interest that can transmit
acoustical information to stationary unit 130, and optionally,
stationary unit 130 need not be in communication with a portable
unit.
[0181] When the subject is an adult who does not require an
attendant, a portable unit may be unnecessary, The enunciation of
acoustical information A by detector unit 20 or of warning signal W
by stationary unit 130 will advantageously stimulate the subject to
awake during manifestation of sleep apnea.
[0182] FIG. 16A illustrates a block diagram of detector unit 20.
Detector unit 20 comprises microcontroller 43, e.g. the PIC-16xxx
family of microcontrollers, which is provided with memory device
112, such as Read-Only Memory (ROM) or Non-Volatile Random Access
Memory (NVRAM), for storing therein firmware algorithms such as an
algorithm for the detection of apnea, as will be described
hereinafter, Random Access Memory (RAM) 114 including registers,
event log 116, such as based on NVRAM, and digital signal processor
118. Microcontroller 43 receives input from sensors 115, including
apnea sensors and additional sensors, such as urine sensor, feces
sensor, ambient temperature sensor, humidity sensor, illumination
level sensor, body temperature sensor, body activity sensor,
oximeter, and infant sleeping orientation sensor, from analog
interface 119, Analog to Digital (A/D) converter 121, and from
battery level detector 123 connected to battery 49. Microcontroller
43 is also in communication with deactivation button 45, display
122, LEDs 124, enunciator 125, timer 127, e.g. an interrupt timer,
and external data interface 129. Detector unit 20 is adapted to
couple with docking port 135, which may be integrally attached to
the stationary unit or may be an independent docking unit, to
facilitate the retrieval of data stored in event log 116 by means
of data interface 129, to charge battery 49, or to upgrade firmware
112.
[0183] FIG. 16B illustrates an exemplary method for detecting
apnea. The microcontroller of the detector unit receives signals
from the corresponding apnea sensor, whether a capacitive type
sensor or a curvature sensor as described hereinabove. The received
signals are representative of a value of a parameter that is
characteristic of the breathing patterns of a subject. The
microcontroller processes the received characteristic breathing
pattern values (CBPVs) by means of the firmware algorithm stored in
the memory device and determines whether the CBPVs are indicative
of the onset of apnea.
[0184] To minimize the consumption of battery power, the
microcontroller operates at a low periodic sampling rate of e.g. 1
sample per 250 msec when receiving CBPVs, and is in a low-power
inactive mode during the interval between two sampling operations.
Even though the microcontroller is in the inactive mode, the LEDs
of the detector unit are generally periodically lit to indicate
that the detector unit is in operation. It will be appreciated,
however, that the microcontroller can also be continuously
operated, if so desired. The microcontroller is initialized during
initial powerup, and is able to differentiate setup operations
between the initial powerup time and a periodic powerup time. A
register may be used as a counter, and the counter is decremented
in step 140 after each subsequent time interval, e.g. 1 msec, has
elapsed. At the predetermined periodic powerup time, a CBPV is
received in step 142. In addition to CBPVs, other characteristic
parameter values for the performance of auxiliary operations such
as urine detection and battery level detection are received by the
microcontroller at predetermined slower sampling rates, in order
reduce battery consumption.
[0185] The RAM of the microcontroller has three registers: (1) a
shift register in which is stored a plurality of data bits
representative of a previously stored CBPV ("status register" or
STRG), (2) a register in which is stored data bits representative
of a maximum CBPV received during inhalation ("inhalation register"
or INRG), and (3) a register in which is stored data bits
representative of a minimum CBPV received during exhalation
("exhalation register" or EXRG).
[0186] The status register serves as a means for comparing the
breathing patterns of the subject without need of calibration, to
determine whether the onset of apnea has been detected. The least
significant bit (LSB) of the shift register is set to a value of 0
after determining that the presently received CBPV is greater than
the previously received CBPV, indicating that the subject is
inhaling. Conversely, the LSB of the shift register is set to a
value of 1 after determining that the presently received CBPV is
less than the previously received CBPV, indicating that the subject
is exhaling. When a LSB is stored, all of the previously stored
data bits are shifted to the left and the previously stored most
significant bit (MSB) is deleted. By retaining all previously
stored data bits during a predetermined period of time, e.g. 10
seconds, a comparison can be made with the data bits stored in the
status register to determine whether the subject is exhibiting a
regular breathing pattern. That is, a regular breathing pattern is
exhibited when the subject periodically inhales and exhales.
However, if all the stored data bits in the status register are
identical, an abnormal breathing pattern is being exhibited and a
corrective action is needed.
[0187] Accordingly, the microcontroller determines in step 144
whether the LSB of the status register is set to 0. If so, the
microcontroller determines in step 146 whether all data bits stored
in the status register are 0. If all data bits stored in the status
register are 0, the subject has been found not to be exhaling
during the period equal to the product of number of bits and the
interval between two sampling operations, whereupon an alarm flag
is set in step 148.
[0188] If some of the data bits stored in the status register are
1, indicating that a regular breathing pattern is being exhibited,
the presently received CBPV is compared with the maximum CBPV
stored in the inhalation register in step 151. If the presently
received CBPV is greater than the difference between the maximum
CBPV stored in the inhalation register and a characteristic delta
value, which takes into account hysteresis during data acquisition,
such as a result of movement of the infant or partial inhalation,
the LSB of the status register is set to 0 in step 152, the other
bits thereof are shifted to the left and the MSB thereof is
deleted. If the presently received CBPV is greater than the maximum
CBPV stored in the inhalation register as determined in step 154,
the inhalation register is set to CBPV in step 156. However, if the
presently received CBPV is less than the difference between the
maximum CBPV stored in the inhalation register and the
characteristic delta value, a change in the breathing pattern is
being exhibited and the LSB of the status register is set to 1 in
step 158, whereupon the exhalation register is set to CBPV in step
160.
[0189] After determining whether the inhalation register needs to
be set with the CBPV in step 154 or performing steps 156 or 160, a
determination is then made in step 162 whether the alarm flag has
been set. If the alarm flag has been set, a warning sound, which is
preferably an acoustical signature defined by a predetermined
number of tones each of which having a predetermined duration and
frequency, is enunciated in step 164. If the deactivation button is
depressed in step 166, the warning sound will not be enunciated in
step 168.
[0190] This method is similarly performed for exhalation in steps
176, 178, 181, 182, 184, 186, 188, 190 when the LSB of the status
register is set to 1 in step 144. The microcontroller then returns
to the inactive mode in step 170 for another interval prior to
another sampling operation.
[0191] FIG. 17 illustrates a block diagram of stationary unit 130.
Stationary unit 130 comprises microcontroller 195, which is
provided with memory device 192, such as Read-Only Memory (ROM) or
Non-Volatile Random Access Memory (NVRAM), and Random Access Memory
(RAM) 194 including registers, microphone 197 for detecting an
audio signal, e.g. an acoustical signature, emitted by enunciator
125 of detector unit 20 (FIG. 16A), amplifier 198, and audio
bandpass filter (BPF) 199. BPF 199 receives an amplified audio
signal and filters unwanted noise and tones that have a frequency
outside the predetermined frequency band of the detector unit
enunciator. The filtered signals are transmitted as digital inputs
to microcontroller 195. When microcontroller 195 determines that
the filtered signals are indicative of a predetermined audio signal
emitted by the detector unit, a high-volume warning signal W is
generated by means of amplifier 201 and speaker 202, to audibly
alert an authorized attendant that a corrective action needs to be
urgently taken. Alternatively, or in addition, microcontroller 195
may output textual information to display 204, e.g. a liquid
crystal display (LCD), or to optical indicators 205, such as an
LED.
[0192] Microcontroller 195 receives inputs from one or more user
initiated controls 211, such as a dial, button or switch.
Stationary unit 130 is powered by power supply 212 and a suitable
power source, such as battery 214 or by means of alternating
current (AC). Battery 214 may be rechargeable and serve as a backup
during an outage or shortage of power supplied from the AC
mains.
[0193] Data may be exchanged with microcontroller 195 by means of
external data interface 219. Stationary unit 130 is adapted to
couple with docking port 217, to facilitate the retrieval of data
by means of data interface 219, to charge battery 214, or to
upgrade firmware stored in memory device 192. Data interfacing
circuits may interface between docking port 217 and microcontroller
195. These data interfacing circuits may also be connected to a
universal serial bus (USB), a data network such as Ethernet, or to
an Internet service provider such as by an asymmetric digital
subscriber line (ADSL) line. Such data exchange enables the
analysis of event log 116 (FIG. 16A), the upgrading of firmware 192
and/or the updating of configuration information and user settings.
Docking port 217, which may be integrally attached to stationary
unit 130, may be the same docking port to which the detector unit
is coupled, and therefore is adapted to charge detector unit
battery 49 (FIG. 6) and to update detector unit firmware 112 (FIG.
16A).
[0194] When a portable unit is employed, microcontroller 195 also
comprises a transceiver 205 for transmitting a wireless signal
S.sub.1 over a cellular network and a transceiver 206 for
transmitting an RF signal S.sub.2. A signal S.sub.1 or S.sub.2,
depending on with which network the portable unit is in
communication, is transmitted to the portable unit when a
corrective action needs to be taken. Alternatively, a signal
S.sub.1 may be transmitted over a cellular network to a
predetermined number to alert the authorized adult who is not in an
audible range of stationary unit 130 or to an emergency medical
service, such as when the infant is exhibiting symptoms of SIDS,
particularly sleep apnea. Alternatively, a signal S.sub.1 or
S.sub.2 may be transmitted to a home automation system, for
activating a device to alert an authorized attendant who may be
asleep or does not respond to a high-volume warning signal W or to
a cellular telephone call. The home automation system may turn on,
or flash, lights, or actuate a vibrator to ensure that the
authorized attendant will take emergency corrective actions.
[0195] Stationary unit 130 may also amplify acoustical information
enunciated by the subject. The acoustical information which is
received by microphone 197 is amplified and emitted by speaker 202,
or transmitted by transceiver 205 or 206.
[0196] FIG. 18 illustrates a block diagram of portable unit 140.
Portable unit 140 comprises RF transceiver 222, speaker 225, and
battery 227, e.g. a rechargeable battery, for powering portable
unit 140. Battery 227 may be recharged by docking port 239, which
may the same docking port used for the stationary unit or a
separate charger. Transceiver 222 receives wireless signal S.sub.2
when transmitted by the stationary unit. Wireless signal S.sub.2 is
then enunciated by means of speaker 225. Alternatively, portable
unit 140 may comprise a cellular transceiver (not shown) for
receiving a wireless signal via a cellular network.
[0197] Portable unit 140 may also comprise microphone 231 and
Push-to-Talk (PTT) button 232. When the authorized attendant who is
accessible to portable unit 140 desires to vocalize voice
information, e.g. soothing words of comfort to an infant, PTT
button 232 is depressed, and microphone 231 transmits the voice
information to transceiver 222, which transmits the same as signal
V to transceiver 206 (FIG. 17) of the stationary unit. The voice
information is therefore able to be enunciated by speaker 202 (FIG.
17) of the stationary unit and heard by the infant.
[0198] In one embodiment, portable unit 140 also comprises
microcontroller 237 and display 234, e.g. an LCD. A wireless status
signal S.sub.2 indicative of a subject related parameter of
interest can be transmitted from the stationary unit to transceiver
222, which is subordinate to microcontroller 232. A relevant
subject status can be displayed on alphanumeric display 234, or by
means of optical indicators, e.g. LEDs.
[0199] FIG. 19 illustrates another embodiment of a subject
monitoring system, which is designated by numeral 240. In the
example of FIG. 19, detector unit 20 is configured to emit a sound
or audio signal (for example, of known or predetermined sound
contact)--for example, detector unit 20 includes a speaker. The
audio signal (i.e. `alert signal` contingent upon a detected
presence of a symptom of apnea or another detected condition of the
subject) is then detected by a sound-detection unit (which may be
stationary or portable--in FIG. 19 it is illustrated as `stationary
unit`) that is deployed within audible range of the detector unit
20 (e.g. at least 2 meters or 5 meters or 10 meters and/or at most
100 meters or 20 meters or 10 meters). Sound detection unit 130
includes a microphone configured to detect sound and to generate an
electrical signal descriptive of the detected sound. In addition,
the system 240 may include electrical circuitry (i.e. including any
combination of digital or analog electrical hardware and/or
software/executable computer code--for example, including one or
more microprocessors, volatile and/or non-volatile memory, and/or
executable code stored in memory) configured to analyze the
electrical signal descriptive of the detected sound and to
determine if the electrical signal descriptive of the detected
sound matches the pre-determined and/or known audio alert signal.
This allows for distinction between ambient noise and other noise
and noise specifically emitted by detection unit 20. This
electrical circuitry may be deployed in any location--for example,
as part of unit 130 or in any other location.
[0200] System 240 may also include an alert signal-emitting unit
(e.g. including a speaker or visual display or digital computer
configured to sent an electronic communication) configured, in
response to the results of the analysis by the electrical
circuitry, and contingent upon a positive matching (i.e. a
determination that the electrical signal descriptive of the
detected sound from the microphone does match the sound
characteristics of the audio alert signal), to emit one or more
additional alert signals.
[0201] In some embodiments, the alert signal emitting unit and the
sound detection unit are provided a a single unit 130 and co-reside
in the same housing. It is appreciated that this is not a
limitation, and other implementations are possible.
[0202] In one example, the additional alert signal is an additional
audio alert signal. In another example, the additional alert signal
may be visual alert signal. In yet another example, the additional
alert signal may be provided by an electronic communication such as
an email, a text message (e.g. an SMS), or a communication via a
packet switched and/or internet network. In yet another example,
the additional alert signal may be a radio signal or infra-red data
communication.
[0203] System 240 may also include an additional portable unit 150
and/or override unit 250 in communication with alert
signal-emitting unit 130
[0204] As shown in FIG. 20, override unit 250 comprises RF
transceiver 242 and video frame generator 247. Override unit 250 is
connected to set-top box 251, the function of which is well known
to those skilled in the art and which is also connected to home
entertainment system 255. When signal S.sub.2 is received by
transceiver 242, the display of a program via set-top box 251 and
home entertainment system 255 is temporarily interrupted, whereupon
a predetermined video frame is displayed on home entertainment
system 255. When signal S.sub.2 is a warning signal or is based on
voice information vocalized by the infant, the voice information
can be heard on home entertainment system 255. If so desired,
override unit 250 may be used to actuate a home automation system,
for activating a device to alert an authorized attendant.
[0205] While some embodiments of the invention have been described
by way of illustration, it will be apparent that the invention can
be carried out with many modifications, variations and adaptations,
and with the use of numerous equivalents or alternative solutions
that are within the scope of persons skilled in the art, without
departing from the spirit of the invention or exceeding the scope
of the claims.
* * * * *