U.S. patent application number 14/449499 was filed with the patent office on 2014-11-27 for method and circuit for storing and providing historical physiological data.
The applicant listed for this patent is COVIDIEN LP. Invention is credited to Michael E. Fein, Paul D. Mannheimer.
Application Number | 20140350415 14/449499 |
Document ID | / |
Family ID | 26923457 |
Filed Date | 2014-11-27 |
United States Patent
Application |
20140350415 |
Kind Code |
A1 |
Mannheimer; Paul D. ; et
al. |
November 27, 2014 |
METHOD AND CIRCUIT FOR STORING AND PROVIDING HISTORICAL
PHYSIOLOGICAL DATA
Abstract
Embodiments of the present invention include systems and methods
that relate to pulse oximetry. Specifically, one embodiment
includes an oximeter sensor comprising a light emitting element
configured to emit light, a light detector configured to detect the
light, and a memory chip having a built-in trimmed resistor, the
trimmed resistor having a resistance value that is detectable by a
monitor.
Inventors: |
Mannheimer; Paul D.;
(Danville, CA) ; Fein; Michael E.; (Mountain View,
CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
COVIDIEN LP |
Mansfield |
MA |
US |
|
|
Family ID: |
26923457 |
Appl. No.: |
14/449499 |
Filed: |
August 1, 2014 |
Related U.S. Patent Documents
|
|
|
|
|
|
Application
Number |
Filing Date |
Patent Number |
|
|
11445042 |
Jun 1, 2006 |
|
|
|
14449499 |
|
|
|
|
10452806 |
May 30, 2003 |
|
|
|
11445042 |
|
|
|
|
09943899 |
Aug 30, 2001 |
6606510 |
|
|
10452806 |
|
|
|
|
60299616 |
Jun 20, 2001 |
|
|
|
Current U.S.
Class: |
600/483 |
Current CPC
Class: |
A61B 5/14551 20130101;
A61B 5/11 20130101; A61B 5/053 20130101; A61B 2562/085 20130101;
A61B 5/7232 20130101; A61B 5/0205 20130101; Y10S 323/911 20130101;
A61B 5/1495 20130101; A61B 5/02055 20130101; A61B 5/14552 20130101;
A61B 5/74 20130101; G01D 18/00 20130101 |
Class at
Publication: |
600/483 |
International
Class: |
A61B 5/00 20060101
A61B005/00; A61B 5/11 20060101 A61B005/11; A61B 5/053 20060101
A61B005/053; A61B 5/0205 20060101 A61B005/0205 |
Claims
1. A device wearable by a patient, comprising: a disposable
connection component comprising at least two electrodes configured
to generate an impedance measurement, the at least two electrodes
configured to attach to the patient via an adhesive; a
nondisposable component configured to be removably coupled to the
disposable connection component comprising: a battery; an
accelerometer configured to collect data indicative of a presence
of patient motion; a memory configured to store: a plurality of
physiological characteristics indicative of a status of the patient
in a digital format, the plurality of physiological characteristics
comprising at least data indicative of one or more of an
electrocardiogram (ECG) waveform, data indicative of heart rate,
the data indicative of a presence of patient motion, or any
combination thereof; and at least one indication of one or more
events; an interface configured to transmit at least one of the
plurality of physiological characteristics to a remote device; and
a light indicator configured to provide a light signal indicative
of an operating status of the device.
2. The device of claim 1, wherein the nondisposable component is
configured to be used a plurality of times on a plurality of
patients.
3. The device of claim 1, wherein the nondisposable component is
configured to be used at home by the patient and subsequently
provided to a caregiver.
4. The device of claim 1, wherein the memory is further configured
to store a patient identification.
5. The device of claim 1, wherein the memory is further configured
to store an indication of patient temperature.
6. The device of claim 1, wherein the memory is further configured
to store an indication of ambient temperature.
7. The device of claim 1, further comprising a display.
8. The device of claim 1, further comprising a visual alarm
indication.
Description
[0001] This application is a continuation of U.S. patent
application Ser. No. 11/445,042, filed Jun. 1, 2006, which is a
continuation of U.S. patent application Ser. No. 10/452,806, filed
May 30, 2003, which is a divisional application of U.S. patent
application Ser. No. 09/943,899, filed Aug. 30, 2001, which issued
as U.S. Pat. No. 6,606,510 and claims the benefit of U.S.
Provisional Application Ser. No. 60/299,616, filed Aug. 31, 2000,
all of which are incorporated herein by reference.
BACKGROUND
[0002] Pulse oximetry is typically used to measure various blood
flow characteristics including, but not limited to, the blood
oxygen saturation of hemoglobin in arterial blood, the volume of
individual blood pulsations supplying the tissue, and the rate of
blood pulsations corresponding to each heartbeat of a patient.
Measurement of these characteristics has been accomplished by use
of a non-invasive sensor that passes light through a portion of a
patient's blood perfused tissue and photo-electrically senses the
absorption and scattering of light in such tissue. The amount of
light absorbed is then used to estimate the amount of blood
constituent in the tissue. The "pulse" in pulse oximetry comes from
the time varying amount of arterial blood in the tissue during the
cardiac cycle. The signal processed from the sensed optical signal
is a familiar plethysmographic waveform due to cycling light
attenuation.
[0003] To estimate blood oxygen saturation of a patient,
conventional two-wavelength pulse oximeters emit light from two
light emitting diodes (LEDs) into a pulsatile tissue bed and
collect the transmitted light with a photodiode (or photo-detector)
positioned on an opposite surface (i.e., for transmission pulse
oximetry) or an adjacent surface (i.e., for reflectance pulse
oximetry). One of the two LEDs' primary wavelength is selected at a
point in the electromagnetic spectrum where the absorption of
oxyhemoglobin (HbO.sub.2) differs from the absorption of reduced
hemoglobin (Hb). The second of the two LEDs' wavelength is selected
at a different point in the spectrum where the absorption of Hb and
HbO.sub.2 differs from those at the first wavelength. Commercial
pulse oximeters typically utilize one wavelength in the near red
part of the visible spectrum near 660 nanometers (nm) and one in
the near infrared (IR) part of the spectrum in the range of 880-940
nm. The amount of transmitted light passed through the tissue will
vary in accordance with the changing amount of blood constituent in
the tissue and the related light absorption.
[0004] An encoding mechanism is shown in U.S. Pat. No. 4,700,708,
the disclosure of which is incorporated herein by reference. This
mechanism relates to an optical oximeter probe which uses a pair of
light emitting diodes (LEDs) to direct light through blood perfused
tissue, with a detector picking up light which has not been
absorbed by the tissue. The operation depends upon knowing the
wavelength of the LEDs. Since the wavelength of LEDs can vary, a
coding resistor is placed in the probe with the value of the
resistor corresponding to the actual wavelength of at least one of
the LEDs. When the oximeter instrument is turned on, it first
applies a current to the coding resistor and measures the voltage
to determine the value of the resistor and thus the value of the
wavelength of the LED in the probe.
[0005] Oxygen saturation can be estimated using various techniques.
In one common technique, the photo-current generated by the
photo-detector is conditioned and processed to determine the
modulation ratio of the red to infrared signals. This modulation
ratio has been observed to correlate well to arterial oxygen
saturation. The pulse oximeters and sensors are empirically
calibrated by measuring the modulation ratio over a range of in
vivo measured arterial oxygen saturations (SaO.sub.2) on a set of
patients, healthy volunteers, or animals. The observed correlation
is used in an inverse manner to estimate blood oxygen saturation
(SpO.sub.2) based on the measured value of modulation ratios of a
patient. The estimation of oxygen saturation using modulation
ratios is described in U.S. Pat. No. 5,853,364, entitled "METHOD
AND APPARATUS FOR ESTIMATING PHYSIOLOGICAL PARAMETERS USING
MODEL-BASED ADAPTIVE FILTERING", issued Dec. 29, 1998, and U.S.
Pat. No. 4,911,167, entitled "METHOD AND APPARATUS FOR DETECTING
OPTICAL PULSES", issued Mar. 27, 1990. The relationship between
oxygen saturation and modulation ratio is further described in U.S.
Pat. No. 5,645,059, entitled "MEDICAL SENSOR WITH MODULATED
ENCODING SCHEME," issued Jul. 8, 1997. All three patents are
assigned to the assignee of the present invention and incorporated
herein by reference.
[0006] Nellcor U.S. Pat. No. 5,645,059, the disclosure of which is
hereby incorporated herein by reference, teaches coding information
in sensor memory used to provide pulse modulated signal, to
indicate the type of sensor (finger, nose), the wavelength of a
second LED, the number of LEDs, the numerical correction terms to
the standard curves, and an identifier of the manufacturer.
[0007] The LEDs and photo-detector are typically housed in a
reusable or disposable oximeter sensor that couples to the pulse
oximeter electronics and the display unit (hereinafter referred to
as the monitor). The sensors are often connected to patients for
long periods of time. Conventionally, historical physiological data
for the patient is collected, if at all, by the monitor coupled to
the sensor. The historical data can be valuable to a clinician or
medical personnel for diagnostic and monitoring purposes. Patients
are often moved to various locations during treatment. For example,
a patient may be picked up in an ambulance, delivered to an
emergency room, moved to an operating room, transferred to a
surgical recovery room, transferred to an intensive care unit, and
then moved to a nursing floor or other locations. Thus, the patient
may be moved between various locations within the same hospital, or
between different hospitals. In many instances, the sensor employed
to monitor the condition of the patient is adhesive in its
attachment and remains with the patient. The monitors, however, are
typically local to particular locations within a facility or
vehicle. The sensor is normally disconnected from the monitor at a
departure site and reconnected to another monitor at a destination
site. Consequently, any patient related data (e.g., historical
physiological data) collected by the monitor at the departure site
is normally unavailable to the clinician attending the patient at
the destination site.
BRIEF DESCRIPTION OF THE DRAWINGS
[0008] FIG. 1 shows a perspective view of an exemplary embodiment
of an oxygen measurement system; and
[0009] FIG. 2 shows a block diagram of an exemplary embodiment of
an oxygen monitor and sensor; and
[0010] FIG. 3 shows a block diagram of a pulse oximeter system
incorporating an exemplary calibration memory element according to
an embodiment.
DETAILED DESCRIPTION
[0011] The present techniques relate to physiological monitoring
instruments and, in particular, sensors that include a mechanism
for storing and providing to a monitor historical physiological
data such as blood oxygen saturation data. Embodiments of the
present invention include pulse oximetry sensors that include coded
information relating to patients.
[0012] The present techniques provide a memory chip for use in an
oximeter sensor, or an associated adapter or connector circuit to
provide enhanced capabilities for the oximeter sensor. The
techniques provide a mechanism for storing and providing patient
related data such as patient trending data, a patient ID or
historical physiological data (e.g., blood oxygen saturation data
for a patient).
[0013] In addition to providing unique data to store in such a
memory, the present techniques include unique uses of the data
stored in such a memory. In a specific embodiment, the patient
related data (e.g., historical physiological data) is stored in a
storage medium that "travels" with the patient and is accessible
wherever the patient is moved. This is achieved by storing the data
within a sensor assembly, (e.g., within the sensor itself, a
connector plug, a connector cable, or an interconnection module).
At the destination site, a monitor or a device capable of
interfacing with the sensor assembly electronics can retrieve and
display the data. The stored data allows a clinician or medical
personnel at the destination site to assess the condition of the
patient for the entire time that the patient has been previously
monitored. The techniques can be used to store and provide various
types of physiological data including, but not limited to, patient
trending data, a patient ID, blood oxygen saturation, heart rate,
blood pressure, and temperature data.
[0014] A specific embodiment provides a pulse oximeter sensor that
includes a number of light sources, at least one photo-detector,
and a memory circuit associated with the sensor. The light sources
are selected to operate at different wavelengths. The
photo-detector receives light emitted by the plurality of light
sources. The memory circuit stores patient related data. For
example, the memory circuit stores physiological data derived from
the detected light and sent to the circuit by an oximeter monitor,
and the circuit then provides the data later when requested by a
monitor. The physiological data is indicative of a physiological
condition of a patient being monitored by the sensor.
[0015] Another specific embodiment provides a method for storing
patient related data (e.g., physiological data). The method
detects, via a sensor, at least one signal indicative of a
physiological condition, and conditions the detected signal to
generate data samples. The data samples are processed to generate
the physiological data, wherein the physiological data describes
the physiological condition. The physiological data is stored
within a memory associated with the sensor. The physiological data
can be coded and compressed before storage to the memory. Other
types of patient data (e.g., patient ID) are stored on the memory
in other embodiments.
Part I
[0016] FIG. 1 shows a perspective view of an exemplary embodiment
of a physiological measurement system 100. System 100 includes a
monitor 110. Monitor 110 couples via an electrical cable 128 to a
sensor 130 that is applied to a patient 132. Sensor 130 includes a
sensor cable 124 and a sensor connecting plug 122. Sensor 130 may
include light sources (e.g., LEDs) and a photo-detector along with
suitable components to couple the electro-optical components to
electrical cable 128. Sensor 130 is shown in FIG. 1 as a clip-on
sensor. However, present embodiments can be applied to many sensor
implementations, including those attached to a patient by adhesive
and other attachment means. In a specific embodiment, monitor 110
is a pulse oximeter and sensor 130 is a pulse oximeter sensor.
However, the sensor may include a temperature, heart rate, blood
pressure, or other type of physiological sensor.
[0017] In an exemplary embodiment, for estimating blood oxygen
saturation, light from light sources at two or more wavelengths
(e.g., red and infrared) is transmitted through a patient's blood
perfused tissues (e.g., in a finger) and detected by a
photo-detector. The selection of the wavelengths is based on a
number of factors. Such factors include the absorption
characteristics of the patient and transmission medium. The light
sources and photo-detector are typically housed within a sensor
that couples to the monitor (e.g., the pulse oximeter). The
detected optical signal is then provided to the monitor for
processing.
[0018] FIG. 2 shows a block diagram of an embodiment of monitor 110
and sensor 130. Within monitor 110, a time processing unit (TPU)
220 provides control signals 222 to an LED driver 224 that, via
data line(s) 226, alternately activates LEDs 230 within sensor 130.
Depending on the particular implementation, LEDs 230 include two or
more LEDs and LED driver 224 provides the drive signals for the
LEDs. When activated, the light from LEDs 230 passes through a
medium (e.g., air or a fiber optic cable, depending on the
implementation) into a patient's tissues 234. After being
transmitted through or reflected from the tissues, the light is
received by a photo-detector 240 via another medium (e.g., air or
another fiber optic cable). Photo-detector 240 converts the
received light into a photo-current, which is then provided to an
amplifier 250 that amplifies the photo-current.
[0019] As shown in FIG. 2, the amplified signal from amplifier 250
is provided to circuitry for two different channels, one channel
for each of the red and infrared wavelengths. For a
three-wavelength implementation, circuitry is provided for three
channels. Each channel circuitry includes an analog switch 252
coupled in series with a low pass filter 254 that is further
coupled in series with an analog-to-digital converter (ADC) 256.
Control lines 258 from time processing unit 220 select the sampled
data from the channel corresponding to the LED being activated.
Specifically, the sampled data from ADC 256a is selected when the
red LED is activated and the sampled data from ADC 256b is selected
when the infrared LED is activated. The sampled data from ADCs 256
is provided to a buffer 260 that stores the data for further
processing. In an implementation, as buffer 260 periodically fills
up, a processor 262 coupled to a bus 264 directs the transfer of
the data from buffer 260 into a memory 266. The monitor
implementation shown in FIG. 2 is one of many implementations. The
present techniques can be adapted for application in various
monitor implementations.
[0020] The sensor 130 may include circuitry that stores historical
physiological data and provides the data when requested. As shown
in FIG. 2, sensor 130 includes a memory 236 coupled to an interface
circuit 238. Interface circuit 238 provides signal conditioning,
and can also provide other functions such as address decoding, and
so on. Interface circuit 238 couples via a bus 270 to a data
interface circuit 268 within monitor 110. Through interface
circuits 238 and 268, physiological data is transferred between
monitor 110 and sensor 130.
[0021] In an embodiment, to enhance compatibility of the present
sensor with conventional sensors and conventional monitors, bus 270
is implemented using new signal lines (i.e., not using or sharing
the existing signal lines of conventional sensors). Bus 270 can be
implemented as a serial bus, a parallel bus, or other bus
architectures. With this implementation, when sensor 130 is plugged
into a monitor not capable of supporting its features, the signals
on interface circuit 238 are simply ignored by the monitor, or
alternatively not requested by the monitor.
[0022] In another embodiment, interface circuits 238 and 268
interact via signal line(s) or wire(s) existing in conventional
sensors and monitors. For example, interface circuits 238 and 268
can couple via data line(s) 226 and time multiplex with the LED
drive signals from LED driver 224.
[0023] Time processing unit 220, buffer 260, processor 262, memory
266, and data interface circuit 268 can be implemented in various
manners. For example, these elements can be implemented within a
single integrated circuit, such as a DMC68HC 16 micro-controller
from Motorola. These elements can also be implemented within an
application specific integrated circuit (ASIC), a digital signal
processor, a microcontroller, or other circuits.
[0024] In one embodiment, patient-specific data such as trending
data or patient monitoring parameters can be actively stored in the
memory 236 (e.g., a memory chip). As the patient and sensor travel
from ward-to-ward of the hospital, and consequently plug into
different oximeters, the patient-specific data can be read from
memory 236 of the patient's dedicated sensor and displayed on a
display screen for viewing or used by the oximeter monitor for
other purposes. Memory 236 may, for example, be implemented as a
random access memory (RAM), a FLASH memory, a programmable read
only memory (PROM), an electrically erasable PROM, a similar
programmable and/or erasable memory, any kind of erasable memory, a
write once memory, or other memory technologies capable of write
operations. Examples of patient specific data that can be stored in
memory 236 are now discussed.
[0025] Patient trending data regarding the history of a patient's
blood oxygen saturation (SpO.sub.2) level, pulse rate, pulse
amplitude, perfusion data, and other patient data over a period of
time can be recorded in memory 236. The oximeter monitor can
continuously or periodically store a patient's current trend data
into memory 236 to maintain a historical data for the patient. The
memory can be erased and overwritten multiple times. For example,
the patient trend data can be erased from memory 236 each time a
sensor is used on a new patient (e.g., each time the oximeter
monitor is turned off or when user input to the monitor indicates a
new patient). This memory characteristic may be advantageous, for
example, for nondisposable sensors that may be used multiple times
on multiple patients. Specific examples of memory devices that can
be erased and overwritten are Flash, EEPROM, battery backed RAM,
and other technologies. Alternatively, the data encoded into memory
236 can be permanent and non-erasable. In a specific embodiment, to
preserve the historical data and prevent accidental erasure, the
sensor memory can be written only once. This memory characteristic
also prevents erasure of the data during sensor operation. Further
details of a Method and Circuit for Storing and Providing
Historical Physiological Data are discussed in U.S. patent
application Ser. No. 09/520,104 to Swedlow et al., filed Mar. 7,
2000, which is incorporated by reference herein in its
entirety.
[0026] As another example, the lowest and/or highest blood oxygen
saturation level, pulse rate, pulse amplitude value, temperature
data, blood pressure, perfusion data, or any other patient data
during the monitored time may be stored in memory 236 by the
oximeter monitor. If desired, the lowest/highest values of these
patient parameters over a past specified monitoring time (e.g., 2
hours, 1 day, etc.) may be recorded in memory 236.
[0027] Expected ranges for patient parameters (such as pulse rate,
pulse amplitude, and blood oxygen saturation level) that are
specific to a particular patient may also be recorded in memory 236
by a clinician. This can be a desirable feature, because the
expected patient trending data can vary significantly for each
patient. The oximeter monitor can compare the expected range for
the patient stored in memory 236 with the monitored patient
trending data to determine if the patient's pulse and blood oxygen
levels are within the expected range for that patient. If the
monitored patient parameter varies outside the patient-specific
range recorded in memory 236, a warning message may be displayed on
the oximeter monitor or an alarm signal may be sounded. If desired,
any variations in the monitored patient parameters from the
expected ranges may be recorded in memory 236 along with a time
stamp.
[0028] If desired, portions of a patient's medical chart and/or
past medical history can be digitally encoded and stored in memory
236 (if sufficient memory space is available) so that this
information is maintained with the patient as he is moved around
and can be easily accessed and displayed using an oximeter monitor
if the patient transferred to a different room or hospital. During
normal operation, when the sensor is plugged into the monitor, the
monitor receives the signal from the photo-detector within the
sensor and processes this signal to obtain the desired
physiological data. In some prior art conventional monitors, the
physiological data is stored in a memory within the monitor and
retrieved at a later time by a caregiver when requested. However,
when a patient is moved to new locations and different monitors are
used, the data stored in the monitor at the previous site is
typically not available at the current site, and the historical
data is unavailable.
[0029] In accordance with the present embodiments, the
physiological data is processed, displayed, and stored in the
monitor in the normal or usual manner. In addition, the data is
compressed and provided to the sensor for storage in the memory 236
associated with the sensor. Alternatively, uncompressed data can be
provided to and stored in the memory 236. When the sensor is later
plugged into another monitor, the new monitor can retrieve the data
stored in the sensor memory, decompress the retrieved data, and
display the decompressed data. In an embodiment, when the sensor is
first plugged into a new monitor, the monitor retrieves and
displays the historical physiological data for the most recent
predetermined period (i.e., the last 20 or 30 minutes). This
predetermined period can be programmed by the clinician or can be
preprogrammed into the sensor memory.
[0030] Alternatively, the monitor can be configured to retrieve and
display the historical physiological data at any time upon request
by a health care giver (or a clinician), by the health care giver
simply activating a control knob on the monitor. The monitor can be
preset so as to automatically retrieve the data upon occurrence of
a predetermined event, such as a sensor being plugged into the
monitor, or can be preconfigured so that the data is only retrieved
upon explicit command by a health care giver.
[0031] The pulse oximeter can keep track of how long a particular
patient has been monitored by the pulse oximeter and can
periodically store that time interval in memory 236 by checking the
elapsed time on a counter. For example, a time stamp of the data
can be stored. In this case, the first data sample includes the
specific time (e.g., date and time) when the data is recorded.
Subsequent data samples can be indicated by the number of epochs
away from the first (or a previous) data sample. The counter may be
a circuit element in the oximeter monitor that is reset each time
the oximeter monitor begins to receive data signals from a sensor
or each time that the oximeter monitor is turned off The time
period that a patient has been monitored by the oximeter sensor may
be displayed on a display screen for viewing.
[0032] The pulse oximeter monitor may also include a digital clock
that keeps track of the current date and time. The date and time
that the oximeter monitor was turned on and the date and time that
the oximeter monitor was turned off may be encoded into the sensor
in memory 236. When the oximeter monitor is turned back on again,
the monitor can display the date and time that it was last turned
on and off It may be desirable for medical personnel to know the
last time that patient's vital signs were monitored by the
oximeter. The sensor memory can also store an indication of a
disconnection of the sensor from the monitor. This data allows the
clinician or medical personnel to delineate the events retrieved
from the sensor memory.
[0033] The oximeter monitor instrument may also write the alarm
limits used with a particular patient into memory chip 236. Alarm
limits are values that represent maximum or minimum values of
patient trending data tracked by the oximeter (such as blood oxygen
saturation, pulse rate, pulse amplitude, etc.) that will trigger an
alarm, because they are considered to be dangerous levels. The
alarm limit values may be encoded in memory 236 by the manufacturer
or by a clinician through the oximeter monitor prior to
operation.
[0034] The oximeter monitor periodically checks the patient's
monitored trending data against the alarm limit values. When one of
the monitored patient parameters reaches the alarm limit value
stored in memory 236, the oximeter monitor triggers an alarm which
alerts medical personnel that a problem may exist. Present
embodiments also allow patient-specific alarm values to be set by
medical personnel through the oximeter and stored in memory 236 so
that as the patient moves from monitor-to-monitor (while the sensor
stays with the patient), the appropriate alarm limits need not be
reset each time on the new monitor. Instead, the alarm limits only
need to be programmed once, or at a later time, whenever the
clinician adjusts alarm limits.
[0035] One or more of the patient trending data including blood
oxygen saturation, pulse rate, and pulse amplitude can be written
to memory 236 along with a time of occurrence whenever an alarm
threshold is crossed. Additional information, such as the readings
for a predetermined time prior to an alarm occurrence can also be
stored, and/or periodic values during the alarm breach can also be
stored in memory 236.
[0036] Currently sensors are placed on patients at one hospital
site and stay with the patient from hospital site-to-site. It would
therefore be desirable to have a patient identification code
(patient ID) such as a unique number carried along in the sensor so
that the record keeping, which occurs at each site, can link the
recorded information with the patient. Without a patient ID stored
in the sensor itself, the tracking has to be done manually.
[0037] Thus, in a further embodiment, the oximeter monitor can
store a patient ID in memory 236 of sensor 130. The oximeter has an
input device such as a keyboard, touch screen, or scanner that
allows a patient ID to be entered and reentered into the oximeter
so that it can be stored in sensor memory 236. With patient
trending information being stored in memory 236 of the sensor 130
as discussed above, it is also desirable to have the patient ID
stored in memory 236 so that as the patient goes from hospital
location to location, the new location's staff can verify that old
trending information stored in memory 236 was indeed obtained from
that particular patient. Medical personnel can check that the
patient ID stored in sensor 130 matches the patient ID on the
patient's chart and other paper documentation to verify that these
medical records correspond to the correct patient. If desired, the
oximeter sensor can be interfaced with a hospital computer network
that maintains a database of patient ID numbers to verify the
identity of the patient and to obtain medical records and other
information for the patient stored on hospital databases. The
patient ID stored in memory 236 provides assurance that any data
read from memory 236 of the sensor is correlated with the patient
they are receiving.
[0038] The pulse amplitude of the measured photoplethysmogram is an
indirect measure of blood perfusion (flow) in the local tissue,
changes in blood pressure, vascular tone, vasoconstriction or
dilation, for example, all have an effect on the pulsatile signal
strength observed with a pulse oximeter. The measured modulation,
or other measurement of perfusion, can be stored in memory 236 for
patient trending purposes. The oximeter can compare current
modulation and perfusion data with older data from memory 236 to
determine patient trends over time. The patient's pulse amplitude
deteriorating over time may reflect a serious condition that
demands attention. Therefore, it is desirable to store and monitor
changes in a patient's perfusion over time. Also, a maximum or
minimum perfusion limit may be stored in memory 236 that represents
the maximum or minimum value that the patient's measured perfusion
can reach before the sensor needs to be moved, repositioned, or
adjusted in some other way. The oximeter can trigger a warning
signal or light when a perfusion limit has been reached or a
significant change has occurred.
[0039] The sensor memory can also include a field that indicates
when the sensor memory is full. The information in this field can
be provided to the monitor to direct the monitor to cease sending
data to the sensor memory. The information in this field can be
prominently displayed by the monitor to notify the clinician or
medical personnel. Also, in response, the monitor can generate an
alarm (i.e., blinking light or an audio alarm, or both) to draw the
attention of the clinician to the operating state of the
sensor.
[0040] The sensor memory can also store data for various
physiological characteristics such as, for example, heart rate,
blood pressure, temperature, and so on. For example, the sensor
memory can be used to store NIBP, IBP, and ECG waveforms. Moreover,
as memory costs continue to fall and larger memories become
available, more complex physiological parameters can be measured
and stored.
[0041] Additionally, information about the monitor can be stored or
embedded along with the physiological data. This additional
information may include, for example, the serial number of the
monitor to which the sensor couples, the sensor connect/disconnect
times, monitor diagnostics, and others. This information would
allow the clinician to access historical information on the
instrument as well as the physiological data, which might be
useful, for example, in product liability and malpractice
litigation or in troubleshooting instrument performance
questions.
[0042] The memory 236 associated with the sensor can be physically
located in a variety of places. First, it can be located on the
body of the sensor, in a vicinity of the photodetector, LEDs, or
other sensor components. Or, the memory can be in the sensor
connecting cable 124 or the sensor connecting plug 122, or in an
adapter module that connects to a front of an oximeter, to an
oximeter cable, or to a sensor plug or cable. Whether or not the
memory 236 is in the sensor body, sensor cable 124, sensor plug
122, or adapter module, it is always "associated with" the sensor
since the memory travels with the sensor and patient when the
patient is moved and the sensor is disconnected from the
monitor.
[0043] The monitor and sensor can be configured such that the data
is provided to and stored in the memory 236 automatically and
continuously. The monitor and sensor also employ automated event
recording, such that the monitor in response to an oxygen
desaturation event transfers some of the physiological data to the
sensor memory. Alternatively, particularly when a size of the
memory is small, the monitor can require a user first command the
monitor (e.g., by activating a control knob) to send data to the
memory 236. In this case, valuable storage space in the memory 236
will only be used (and consumed) when the patient being monitored
is believed to be relatively unstable by the caregiver and when it
is believed storage of the historical data for later retrieval may
be particularly desirable.
[0044] As noted above, the techniques can be used to store and
provide various physiological data including, but not limited to,
blood oxygen saturation, heart rate, temperature, and blood
pressure data. For clarity, the invention is described in the
context of the storage and retrieval of blood oxygen saturation
(SpO.sub.2) data. Based on the received signals representative of
the intensity of the light detected by photo-detector 240,
processor 262 estimates oxygen saturation using algorithms that are
known in the art.
[0045] The saturation data for a particular patient is processed by
the monitor attached to the sensor, and the processed data is
provided to the sensor for storage in the sensor memory. The
selection of the sensor memory is dependent on numerous factors
including cost, the amount of data that needs to be stored for a
particular application, the amount of achievable data compression
(if compression is used), the physical dimensions, and so on. For
oxygen saturation, storage of approximately one to seven days of
historical data is adequate for many applications.
[0046] In an embodiment, to reduce the amount of data to be stored
in the sensor memory, the physiological data is compressed before
storage. In an embodiment, the compression is performed by
facilities located within the monitor. Alternatively, the
compression encoding circuit can be on the sensor itself The
monitor further includes facilities to decompress the data later
retrieved from the sensor memory. Compression allows for the use of
a smaller-sized memory in the sensor. This is particularly
advantageous in the case of single patient use disposable sensors
which are typically disposed after use on a patient. Compression
also allows more data to be stored into a memory of a given size.
The ability to store a large amount of data is important for many
diagnostic applications that require data collected over hours or
days.
[0047] The compression scheme can be designed to take advantage of
known characteristics of the physiological data being stored. For
example, it is known that oxygen saturation generally does not
change rapidly. This characteristic can be exploited to achieve
significant compression, as described below.
[0048] For arterial oxygen saturation data, one compression scheme
is based on the realization that saturation data generally exists
in two dimensions, time and absolute saturation value. Saturation
sample time is about one hertz normally, assuming one saturation
value is determined by a monitor for each patient heartbeat. The
number of possible saturation values generally corresponds to 101
possibilities, which assumes each possibility corresponds to an
integer saturation percentage which must lie somewhere between 0%
to 100%. A goal is to use a compression coding technique which
reduces the scope of these two dimensions, which again are 1 Hz by
101 saturation values, to a smaller region, e.g., 0.1 Hz by 8
saturation values, for example, and yet retain the usefulness of
the information. According to one embodiment, Huffman compression
is used with run length encoding, or alternatively or additionally
differential encoding.
[0049] Run length encoding simply means that if the same saturation
value is to be repetitively transmitted, rather than repetitively
transmitting this value, it can be more efficient to count the
number of consecutive times the value occurs, and to instead
transmit the value and the number of times it is repeated.
Differential encoding, though similar, is different in that a
difference between consecutive saturation values to be transmitted
is calculated, and along with the original saturation value one
transmits the differential between adjacent values and the number
of times an identical differential occurs. There are many known
permutations of these two types of common compression techniques
known in the art.
[0050] As noted above, if saturation percentages were to be reduced
to a group of eight values, any single value would correspond to a
range of saturation percentages. For example, ten values could be
selected, with each value corresponding to an incremental increase
of 10 saturation percentage points. A disadvantage of such a
grouping is that a patient who has a saturation which is toggling
between groups by only one saturation percentage, e.g., toggling
between 89% and 90%, can require a great deal of memory to record
this information since the advantages of run length encoding are
greatly diminished if the identity of the group is repetitively
changing.
[0051] Accordingly, it has been determined that it may be desirable
to utilize saturation values which have saturation percentages
which overlap. For example, eight saturation values could be as
follows:
TABLE-US-00001 Saturation Saturation Value # Range (%) 1 85-100 2
80-90 3 75-84 4 70-79 5 65-74 6 60-69 7 1-64 8 0
[0052] Since these saturation values have saturation percentages
which overlap, toggling at a boundary between values 1 and 2 is
prevented for small saturation changes. For example, if value 2 has
previously been stored based on a saturation of 90%, and the
saturation moves to 91%, the saturation range will now correspond
to value 1, and this value will be maintained until the patient
saturation falls below 85%. Hence, with overlapping values or
groups, it is readily apparent the advantages of run length
encoding will be more readily achieved for all patients except the
most unstable whose saturation varies by relatively large amounts
in relatively short periods of time.
[0053] Turning to the other dimension involved with saturation,
specifically saturation sampling frequency, for a sampling rate of
0.1 Hz, a single saturation value can be determined for a patient
based upon their average saturation every 10 seconds. Lower
sampling frequencies could be used which generate less data, which
consume less memory, but a disadvantage is that correspondingly
less information will be stored in the memory. Conversely, higher
sampling frequencies could be used which result in more information
being stored in the memory, with a corresponding disadvantage that
more memory is required.
[0054] Regardless of the saturation sampling frequency, and the
number of saturation values or groups which are used, further
compression can be achieved by overlaying Huffman encoding
techniques, which simply means that if a mean value to be
transmitted is relatively high, such as 95, this value can be
normalized to 0 using Huffman encoding techniques with the result
that fewer bits are required to transmit relatively large numbers
by such normalization.
[0055] Several compression embodiments have been described for
oxygen saturation data. Although present embodiments can be
practiced without the use of compression, additional capabilities
are provided by the judicious use of compression. As used herein,
compression includes any processing that alters, however slightly,
the original form of the physiological data as they are generated
(in the nominal manner) by the monitor. Other compression schemes
can also be used and are within the scope of the invention. Of
course, no compression could be used.
[0056] As noted above, in a specific embodiment, the sensor memory
is implemented as a write-once memory device. A field in the sensor
memory can be set when the sensor is reprocessed so that the
monitor can determine that it is coupled to a reprocessed sensor.
The monitor can use the information in this field to disable the
display of the historical data (for example, if the memory is write
once and relatively full). Alternatively, if the memory is
erasable, a field for storing historical physiological data could
be erased during sensor reprocessing.
[0057] Disabling the data display may be preferable in some
applications to ensure the integrity of the collected data. For a
memory device that can be written once and has a fixed memory size,
it may not be possible to determine where the "old" data came from
or how much memory may still be available on a reprocessed sensor.
Moreover, it is highly desirable to avoid having data from an old
patient being displayed and potentially mistaken as valid data for
the patient to which the sensor couples. Since it is not easy to
control or determine the amount of available unwritten memory after
a use, which can vary from zero to the full amount, inconsistency
and potential customer dissatisfaction may result from using a
sensor having widely varying amounts of available memory. By not
displaying data from reprocessed sensors, these potential problems
are avoided.
[0058] Embodiments may provide advantages not available in
conventional monitors and sensors. For example, certain present
embodiments allow for monitoring of a patient in transit who may be
connected to two or more monitors over a period of time. One such
situation is a patient who is transported in an ambulance to an
emergency room and later transferred to an intensive care unit.
This technique is especially beneficial in this application since
this particular patient is more likely to be in need of close
monitoring and recent historical physiological information.
[0059] Present embodiments can also be used to document
physiological characteristics. For example, for a patient in home
care who requires oxygen, documentation of oxygen saturation is
typically needed. In this case, the sensor of the invention can be
used to store saturation data for the patient over a predetermined
time period (i.e., one week). At the end of this period, the
caregiver can simply remove the sensor and send it away as
documentation of the patient's saturation. These techniques can
also be used to collect data for other applications such as, for
example, sleep diagnostics, de-saturation, and so on.
[0060] The sensor in accordance with present embodiments has been
described for use in combination with a monitor that performs the
signal processing of the detected signal and compression of the
processed data. In another embodiment, the sensor of the invention
includes the facility to process (and compress, if necessary or
desirable) the detected signal. This embodiment advantageously
allows for independent operation of the sensor without support from
a monitor. The data stored within the sensor can be provided to a
monitor for display. The amount of signal processing and
compression that can be achieved by circuitry within the sensor is
only limited by the available technology, which inevitably improves
over time. In the near term, physiological data that does not
require extensive signal processing and compression (e.g.,
temperature, peak amplitude in a waveform, heart rate, and so on)
can be collected and stored by the sensor.
[0061] FIG. 3 is a block diagram of a pulse oximeter system
incorporating a calibration memory element 302 in accordance with
embodiments of the present invention. In one embodiment, memory
element 302 is a two-lead semiconductor digital memory chip. The
calibration element 302 is part of a sensor 304 which also includes
red and infrared LEDs 306, along with a detector 308. If desired,
LEDs 304 may be replaced with other light emitting elements such as
lasers.
[0062] The oximeter includes read circuit 310, drive circuit 312,
look-up tables 314 and 316, controller 318, amplifier 320, filter
322, and analog-to-digital converter 324. Read circuit 310 is
provided for reading multiple coded values across the two leads
326, 328 connected to calibration element 302. One value is
provided to a look-up table 314 to determine appropriate wavelength
dependent coefficients for the oxygen calculation. The other
value(s) are then provided to another look up table(s) 316 which
provides input (e.g., coefficients) to other calculations performed
by controller 318. These additional calculations may enhance the
performance and/or safety of the system. Controller 318 provides
signals to a drive circuit 312, to control the amount of drive
current provided to LEDs 306.
[0063] Detector 308 is connected through the amplifier 320 and the
filter 322 to the A/D converter 324. This forms a feedback path
used by controller 318 to adjust the drive current to optimize the
intensity range of the signal received. For proper operation the
signal must be within the analog range of the circuits employed.
The signal should also be well within the range of A/D converter
324. For example, one rule that may be applied is to adjust LED
drives and amplifier gains so that both red and IR signals fall
between 40% and 80% of full scale reading of converter 324. This
requires correct and independent settings for both the red and
infrared LEDs.
Part II
[0064] Embodiments of the present technique include the
following:
Sensor Model ID
[0065] Encoded text of the specific model of sensor would allow the
instrument to display a text string indicating what sensor is being
used, e.g. "Nellcor OXISENSOR II D-25" or "Adult Digit Sensor" or
"Agilent N-25". Alternately, a sensor code could be stored that
points to a lookup table of display text. Encoding sensor model ID
could also be used to accommodate sensor-specific operating
parameters such as LED drive currents or "sensor off"
characteristics (as an alternative to programming the value of
drive current or "off" characteristics themselves).
Sensor Model--Specific Information
Coefficients for Taylor's Series Calibration Curves
[0066] The sensor may store a general polynomial curve. Other
families of polynomials, such as Tchebyschev polynomials, could be
used as well. This may also pertain to other calibration
information, such as temperature calibration and force transducer
calibration. This allows new sensor types (such as a sensor with an
offset emitter and detector).
Sensor Adjustment/Re-Application Light Levels
Sensor Off Light Levels
[0067] Under normal operating conditions, photosignals coming from
the sensor LEDs generally fall within a certain range. When a
sensor is removed from a patient, or falls off on its own, the
photosignal usually changes. This is particularly true for the
reusable clip-style sensor, since in their normal disconnected
state, the LEDs shine directly onto the photodetector unimpeded by,
for example, tissue. By programming a "threshold photocurrent" into
the memory chip, reliable detection of a "sensor is off the
patient" condition can be accomplished (in this example, exceeding
a certain detected light level is a sure sign the sensor is not on
a finger or other opposed site). For certain other sensors, a low
light level may be indicative of the sensor being off (an adhesive
sensor, for example, lays flat when in its natural state, so little
LED light may reach the detector). Encoding an expected range of
light levels for the specific model of sensor being used allows
enhanced detection of when the sensor is improperly placed or has
been removed.
Temperature at Which to Switch to STORM Algorithm
[0068] The STORM algorithm here refers to the sensors designed to
be used where "motion provides the signal", i.e., the cardiac pulse
need not be present or discernible in order for the oximeter to
provide SpO.sub.2 values. Instead, the red and IR waveforms
resulting from the motion itself are used for determining the
arterial saturation. This feature is possible for tissue beds that
are well "arterialized" (a large supply of arterial blood relative
to the metabolic needs of the tissue) resulting in a small
aterio-venous saturation difference, as well as other signal
characteristics that are not germane to this discussion. It has
been observed that the necessary degree of arterialization
correlates well to being "well perfused" at the tissue site, which
itself correlates well to the tissue bed being warm. Thus by
monitoring the temperature of the skin at the sensor site, and by
knowing a value of temperature (programmed into the memory chip) at
which the "motion-is-signal" algorithm can be utilized for the
specific sensor design being used, improved reading accuracy
through motion can be better accomplished.
Additional Information on Use of Pins
Contact Switch--Sensor Off
[0069] Similar to the contact electrodes of the Nellcor FS-14 fetal
sensor, an extrinsic probe of skin contact can be used to indicate
whether the sensor is in adequate contact to the patient. This
extrinsic probe could be accomplished, for example, through an
impedance measurement across two electrodes, a force or pressure
switch that is sensitive to whether adequate force or pressure is
present in the sensor placement, or through other means. Dedicated
sensor connector pins, or pin-sharing, could be used to accomplish
this additional measure of sensor-patient contact.
Chemical Sensor for EtO Cycles
[0070] An electro-chemical or thermal device that senses and stores
to memory the number of exposures (zero, once, or potentially more
than once or the actual number) to sterilization cycles could be
used to capture the history of the sensor. Excessive exposure to
sterilization cycles degrades a number of components in the sensor,
and can affect its performance. A sensor exceeding a certain number
of exposures could cause a display to indicate the sensor needs to
be replaced.
Sensor Expiration
[0071] This need not be a separate device, but the memory could
contain a date after which time the sterilization can no longer be
certified as being effective. Sterilization can be sensed and the
date recorded automatically by the sensor itself.
Sensor Expiration Date/Sensor Parking: Meter
[0072] At the time of manufacture, the expiration date of the
sensor may be written into the memory chip. The memory-enabled
instrument would then do something with this knowledge (e.g.,
indicate "expired sensor", or refuse to function if expired).
Alternately, the elapsed time of sensor usage could be tracked in
the memory chip (written to it by the instrument) and the sensor
would "expire" after a memory programmed maximum (greater for
reusable sensors than for single-use sensors).
Auto Shut-Off
[0073] After sensor expiration, the instrument may refuse to
function with this sensor and would indicate that a fresh sensor is
needed. Furthermore, the sensor could be disabled by running a high
current through it, or by other means.
Warranty Date
[0074] Similar to the expiration date, the date of expiration of
the sensor warranty could be written into the memory chip (e.g., 2,
or 6, or 12, etc. months from the date of 10 manufacture or the
date of first use). The instrument would give some indication of
this as appropriate.
Patient Specific Information (Written to Sensor from Monitor)
[0075] Trending and/or data logging of patient monitoring
parameters may be stored in the memory of the memory chip. As the
patient and sensor travel from ward-to-ward of the hospital, and
consequently plug into different oximeters, the patient-specific
data could be displayed as it is contained in the patient's
dedicated sensor. Examples of the type of data are given below:
Trending
Low High Sat
[0076] The lowest and/or highest SpO.sub.2 value during the
monitored time, or the lowest/highest values over the past
specified monitoring time (e.g., 2 hours, 1 day, etc.)
Duration of Monitoring
[0077] How long has the patient been monitored by the pulse
oximeter? (elapsed time counter).
Beginning and End of Monitoring
[0078] Clock time of when the monitor was turned on and off.
Pre-Set Alarm Limits
[0079] The alarm limits used with this patient become written to
the memory chip by the instrument. This allows patient-specific
alarm values to be set and memorized so that as the patient moves
from monitor-to monitor (the sensor staying with the patient), the
appropriate alarm limits need not be reset each time on the new
monitor. Instead, this only needs to happen once, or whenever the
clinician adjusts alarm limits.
Changeable Key
[0080] Data encryption utilizes private and/or public keys to
scramble the data written to the memory chip and later decipher the
data so that only authorized devices are supported. To further
prevent the use with a monitor that is not certified to provide
correct results, the sensor manufacturing system could periodically
change the private and/or public keys. The change in the key could
be communicated to the instrument via the memory chip in encrypted
form. The purpose of this feature is to elevate the level of
security in the memory system.
Monitor Code Upgrades From Modem or Sensor
[0081] Distributing code updates in memory. Whenever an oximeter
notes that a code update field is present in the sensor, it would
check whether the proposed update had previously been installed,
and (if not) whether any indicated prerequisites were present (e.g.
a code patch might not function properly in the absence of a
previously-circulated patch). If appropriate conditions are met,
the code upgrade would be installed. If prerequisites are missing,
a message would be displayed to the user, telling him how to obtain
the prerequisites (e.g. call Nellcor).
Black Box Encoder (Patient History, Serial Number of Box. Etc.)
[0082] Use the memory as a general-purpose carrier of patient data,
covering not just oximetry but a lot of other information about the
patient.
Optical Efficiency Correction
[0083] If it is desirable to know where a particular patient lies
in COP space, it is useful to know the inherent brightness of LEDs,
sensitivity of detector, and anything else about the particular
sensor assembly (e.g. bandage color and alignment) that will affect
the amount of light which the sensor receives. Given that
information, a measure of the patient's optical transmissivity may
be computed for each LED wavelength, which depends almost entirely
on the properties of the patient. Signal to noise ratio of the
oximeter is probably determined by the size of the detected signal,
not by the transmissivity of the patient alone. This could take
advantage of DC transmissivity of the tissue to improve the
accuracy of pulse oximetry.
[0084] Another reason for recording LED and detector parameters in
the sensor memory is to provide a basis for later research on the
drift of these parameters due to various environmental conditions
which the sensor experiences. Parameters of interest include not
only LED power and detector sensitivity, but also LED wavelengths,
FWHM, and secondary emission level.
Pigment Adjustment Feature
[0085] For some types of sensors, the accuracy of the sensor may be
different for patients with different skin color. The sensitivity
of accuracy to skin color may depend on sensor model. The sensor
might contain a sensitivity index, indicating how large an
adjustment in readings should be made as a function of skin color.
Skin color might be obtained by user entry of the data (e.g. menu
selection). Another option would be for the sensor to measure skin
color. One way to achieve the latter option would be to provide
transmission sensors with auxiliary detector for "reflected" light.
In combination with the optical efficiency information noted above,
the signal levels reported by the auxiliary detector would sense to
what extent the patient's skin was affecting red and IR pathlengths
differently, and hence to what extent readings needed to be
corrected.
Accelerometer on Chip
[0086] This might be used in a scheme in which the memory chip was
on the bandage, not in the connector. This combines a MEMS
accelerometer with any of several different chips that might
usefully be placed in the sensor head, local digitizing chip,
preamp chip, memory chip.
[0087] Accelerometer data may be used to warn of the presence of
motion (in which case special algorithms may be called into play or
oximetry may be suspended), or actually to help correct for motion
(to the extent to which we can produce algorithms which can predict
physio-optic effects of known motion).
Optical Shunt
[0088] The amount of optical shunting could be measured for each
sensor, or family of sensors. The value would be stored in the
sensory memory for the monitor to read and use to adjust the
processing coefficients.
Monitor Chip Temperature
[0089] The temperature of a red LED, in particular, affects its
principal wavelength, which affects calibration. For one class of
LEDs, the wavelength shifts by about 0.14 nm/C. The memory chip
might contain circuitry capable of monitoring a thermistor or
thermocouple, or the memory chip could be mounted in proximity to
the LED (e.g. under it), so that it could sense directly the
temperature of the LED, and provide a calibration correction
accordingly.
Monitor Ambient Temperature
[0090] This might be used, e.g., in overseeing the operation of a
warmed ear sensor. There is a thermal cutout in the control system
of the WES, that causes operation to terminate if the sensor goes
over a certain temperature. This is a component for protecting the
patient against burns. If the reason for a high sensor temperature
is that the environment is warm, it could be quite acceptable to
continue oximetry, even though warmer operation would be shut down.
In the absence of knowledge about environmental temperature, a high
temperature reading might have to be assumed to mean that something
was wrong with the sensor, in which case all operation might have
to cease. An environmental temperature sensor in the plug could
help to tell which rule to apply. Again, the memory chip could
record the calibration of whatever device was used for
thermometry.
[0091] A passive component on the memory chip could be the
thermometric sensor, and a resistance or voltage measuring device
in the instrument could read out that sensor. Thus, ambient
temperature sensing might not require that large changes be made in
the memory chip.
Temperature Amplifier/Detector
[0092] In illuminating the skin for the purpose of making oxygen
saturation measurements, some heat is generated by the LED
emitters. Tests have been done to establish the maximum safe
current for the LED drive which will assure that the skin
temperature stays within a safe value for the worst case
sensor/patient conditions. This means that in all cases the sensor
will be operated at cooler than the maximum temperature but in most
cases well below the maximum temperature.
[0093] To establish the optimum signal for the measurement, it is
desirable to drive the LEDs with higher current than is imposed by
the above limitations. The temperature amplifier/detector would
allow the LEDs to be driven to a level that still results in a safe
temperature by monitoring the temperature, yet in many cases allow
more drive current, and therefore higher signals, which could give
better readings.
[0094] The inexpensive thermistor devices that could be used in
this application are characterized to allow the measurement to be
accurate. These characterization values could be stored in the
sensor where the thermistor is located. While in operation, the
oximeter would be able to read the characterization values from the
sensor, measure the resistance of the thermistor, and calculate
accurately the temperature of the skin surface where the thermistor
is located. This would keep the patient safe from burns and still
provide the best signal available.
RCAL Resistance Built Into Chip
[0095] In legacy oximetry sensors there is a resistor which is
selected and installed in the sensor connector, to correspond to
the wavelength of the red LED. The wavelength difference from LED
to LED has an impact on the calibration of the saturation
measurement, if not compensated for. The oximeter will read the
value of resistance and adjust its calculation accordingly.
[0096] When adding the memory chip, memory compatible oximeters
will be able to obtain the necessary calibration coefficients from
the memory chip but the legacy instruments will still need a
calibration resistor value. If the resistance were built-in to the
chip and trimmed or selected at manufacture then only one device
would need to be installed in the sensor connector. That would
reduce the overall cost, yet keep the sensor compatible with both
the legacy instruments and the new memory compatible
instruments.
Secondary Emission Measurement
[0097] The oximeter is measuring the relative transmission of the
red and infrared light through the tissue. LEDs have a
characteristic called secondary emission which is indicative of the
amount of light, at wavelengths other than the primary wavelength,
that is being emitted. This characteristic will change the
calibration of the device if not compensated for. It is possible to
make an oximeter that will function within calibration if the
secondary emission is known and compensated for. If the LED were
characterized during manufacture and then the secondary emission
values entered into the memory chip, the oximeter would be able to
read those values and compensate for them so that the sensor was
used properly. This would increase the range of LEDs that could be
used for oximetry, reduce cost and provide better calibration
across a wider range of LED emitters.
Patient ID (Potentially as Tracking Device, Archiving Patient
History, Etc.)
[0098] Currently sensors are placed on patients at one hospital
site and stay with the patient from hospital site-to-site. It would
be helpful to have the patient ID carried along in the sensor so
that the record keeping, which occurs at each site, would be able
to link the recorded information with the patient. Without patient
ID, the tracking has to be done manually. With trend information
being stored in the sensor it also would be desirable to have the
patient ID included so that as the patient went from location to
location, the new location's staff could verify old information and
be assured that it correlated with the patient they were
receiving.
Encode Contact Resistance (e.g. for Oxicliq)
[0099] When making measurements of the resistance that is placed in
the sensor for calibration information purposes, one of the factors
that can influence that measurement is the contact resistance of
the connectors that are between the oximeter and the resistor
itself. In order to compensate for connectors that are significant
in their impact on the measure, one could encode the contact
resistance of the connector and subtract that algorithmically from
the measured resistance to get a more accurate measurement of the
resistance of the calibration resistor. This would enhance the
accuracy with which the resistance measurement is made and,
therefore, make the instrument less prone to inaccuracies in
saturation calculation and display.
Measure Capacitance to Balance Common Mode Rejection
[0100] One of the interfering noise sources that plagues oximetry
is that of common mode noise. This can come from the surrounding
electrical environment. Other instruments, lighters, drills etc.
can produce electrical fields that can couple into the cable
between the patient and the oximeter. Once coupled-in, they can
make measurements more difficult, less accurate, or not possible,
depending on the severity of the noise. To help reduce this common
mode noise, differential amplifiers are used for amplifying the
signal from the sensor. These amplifiers amplify only the
difference between two signal wires. Thus, if the common mode
signal is coupled exactly the same into both wires, the amplifier
will not amplify it because the same signal is present on both
wires.
[0101] If the two wires have different coupling to their electrical
environment, then they will present different signals, and the
difference will be amplified as if it were a signal. One component
that influences this coupling is the capacitance of the lines to
the outside world. This is affected by the manufacture of the
cable, materials, twists in the wire, etc. If one measured the
cables during manufacture and then stored that information in the
memory chip, it could be read when the oximeter is operating. Once
the capacitances for the two wires to the shield are known, the
instrument could be provided with a tunable capacitance device that
would then balance the two lines again and make the noise coupling
to the lines better matched. This would reduce the amount of
susceptibility to the external noise that got coupled into the
patient cable. Reduced noise results in better measurements or the
ability to make measurements at all on some patients.
Fiber-Optic Infrared Wavelength Shift
[0102] The relative wavelengths of the red and infrared light that
is used to make the measurement in oximetry are important to know
so that calibration can be maintained. In traditional LED oximetry,
the LED sources are at the skin so that whatever wavelength is
emitted is what is sensed by the photodiode that receives the
light. The red LED is the only one that we need to characterize for
accurate saturation measurements to be realized. The saturation is
less sensitive to the IR wavelength as long as it stays fixed in
the acceptable range that has been specified for the IR LEDs.
[0103] When using plastic fibers for transmission of the light,
there is a wavelength dependent absorption caused by the fiber.
This has the effect of altering the apparent center wavelength of
the IR source, which can affect calibration of the unit. By
characterizing the fiber for its shift, one could then provide the
proper compensation in the algorithm that calculated the
saturation. This would restore the accuracy that would otherwise be
lost in fiber transmission of the light.
Inform Monitor of Extra LEDs
[0104] There are limitations on the number and type of blood
constituents that can be sensed using the two conventional LED
wavelengths of the oximeter. The accuracy of the oximetry
measurement can also be improved by using different wavelengths at
different saturation ranges. An analysis unit could be developed
that would utilize either or both of these features. To do this, it
would be able to drive additional LEDs. The additional LEDs could
be driven along with the traditional ones or separately. The
oximeter (or additional constituent measurement unit) would provide
the capability to calculate values for these other wavelengths, and
the sensor would provide the additional information to allow the
oximeter to make that calculation. These could be stored in the
memory.
Active Ambient Light Measurement
[0105] One of the problems with oximetry sensors is the
interference caused by ambient light in the environment. This can
be made worse when a sensor comes loose or when the ambient light
is extremely high in value. By characterizing the sensor, one could
know what level of ambient light could be expected or tolerated,
and give a warning to the user when the level has been exceeded.
This would give them the opportunity to adjust the sensor, the
light, or both to affect an improvement in the performance of the
oximeter.
Active Pressure Adjustment for Modulation Enhancement
[0106] The stronger the pulsatile signal, the better the chances
are of measuring the saturation accurately. One way to enhance the
modulation percentage is to apply pressure in the range of the
median pulsatile pressure. If this were implemented, one could use
relatively low cost transducers and supply calibration coefficients
in the memory to allow accurate pressure readings to be made. The
memory could also contain the pressure settings and/or expected
modulation enhancement capability to determine effectiveness of the
pressure enhancement.
Measure Perfusion
[0107] The amount of perfusion affects the amount of modulation,
and thus the AC signal. This affects both the percentage of
modulation vs. the DC amount, and the absolute size of the
modulation. The measured modulation, or other measurement of
perfusion, can be stored in memory for trending or setting limits
on acceptable perfusion before movement or other adjustment of the
sensor is required.
Keep Track of Last Time Sensor Moved or Disconnected
[0108] The time of movement or disconnecting of the sensor could be
written into the memory. Disconnecting can be detected from the
interruption of the signal to the monitor. Moving can be detected
by a sensor off detection, and a subsequent sensor on detection.
Alternately, aggressive movement could be detected and interpreted
as moving of the sensor, or a combination with a sensor off
detection could be used.
Identify Private Label Sensors
[0109] A code can be stored in the sensor memory identifying the
sensor manufacturer. This code can be read and used to indicate
operability with monitors of other manufacturers, or to indicate
any conversion algorithm that may be needed for a signal from a
sensor to be used by a monitor from a different manufacturer. The
code can also be used to allow only supported features to be
used.
Measure Sensor Wetness
[0110] A moisture sensor or impedance sensor can detect the amount
of wetness of the sensor. This can be used for different purposes
and can be stored in the sensor memory for trending or monitoring.
To determine sensor malfunction, the sensor can be disabled if the
wetness exceeds a threshold, which could be stored in the sensor
memory. Some sensors may not provide for isolation of the patient
from the electronics for excessive wetness. The maximum allowable
wetness could be stored in the sensor memory.
Sensor Isolation Indicator
[0111] The sensor memory could identify that the sensor provides
isolation, so wetness is not a concern. Alternately, it could
indicate that isolation is not provided by the sensor, or a limited
amount of isolation is provided.
Low Power Mode Identifier (Sensor Tells Oximeter to Sleep or Wake
Up)
[0112] A portable battery-powered monitor can power down when the
saturation is at a good level, and the patient is stable. Minimal
circuitry in the sensor could be used to do sufficient processing
to tell the monitor when to wake up.
Battery to Run Digital Chip
[0113] A battery can be included in the sensor for a wireless
connection to a monitor. Alternately, a battery could be used to
continue to send data when the monitor is powered down.
Motion Generator ("Thumper")
[0114] The sensor can include a cuff (which inflates and deflates)
or other mechanical mechanism for inducting motion to get a signal
or for inducing pulsitile blood flow to improve the signal.
Sensor Force Indicator (e.g., Too Tight)
[0115] A transducer can measure the amount of force on the sensor.
This can be compared to a maximum value stored in the sensor memory
to determine if the sensor is on too tight. The tightness can also
be recorded and monitored. For example, a patient could swell, and
this could be determined from the trend information and provided as
information to a clinician on a display.
Force Transducer Calibration to Get Pressure
[0116] A calibration value can be stored in the sensor memory for
converting a force measurement into a pressure measurement. A force
transducer can then be used to measure pressure.
Number of Wavelengths
[0117] The sensor memory can store an indication of the number of
wavelengths used in the sensor, and could store the wavelengths
themselves.
Drive Information
[0118] The sensor memory can store information about when to drive
which LEDs. They could all be driven at once, or a subset could be
driven, for example.
Display for Additional Wavelengths
[0119] The memory can store information about what parameters are
to be analyzed and displayed when the extra wavelengths are used.
Oxygen saturation may be displayed when 2 wavelengths are used,
while additional information could be displayed when an extra
wavelength or more are used (Hct, COHb, etc.).
Recycling Times
[0120] Each time a sensor is recycled (sterilized and
reconstructed), a number in the sensor memory can be incremented.
This can be used to prevent operation of the sensor if it has been
recycled more than the allowed number of times (e.g., 3 times).
[0121] While the present invention has been described herein with
reference to particular embodiments thereof, a latitude of
modification, various changes and substitutions are intended in the
foregoing disclosure, and it will be appreciated that in some
instances some features of the invention will be employed without a
corresponding use of other features without departing from the
scope of the invention as set forth. Therefore, many modifications
may be made to adapt a particular situation or material to the
teachings of the invention without departing from the essential
scope and spirit of the present invention. It is intended that the
invention not be limited to the particular embodiments disclosed,
but that the invention will include all embodiments and equivalents
falling within the scope of the claims.
* * * * *