U.S. patent application number 10/667135 was filed with the patent office on 2004-06-24 for radiation detector probe.
This patent application is currently assigned to Exergen Corporation. Invention is credited to Pompei, Francesco.
Application Number | 20040122338 10/667135 |
Document ID | / |
Family ID | 27569568 |
Filed Date | 2004-06-24 |
United States Patent
Application |
20040122338 |
Kind Code |
A1 |
Pompei, Francesco |
June 24, 2004 |
Radiation detector probe
Abstract
Tympanic temperature measurements are obtained from the output
of a radiation sensor mounted in an extension from a housing. The
housing has a temperature display and supports electronics for
responding to sensed radiation. The sensor is mounted in an
improved extension which is shaped to fit into smaller ear canals,
such as a child's ear canal or a swollen adult ear canal. Within
the extension, the sensor is positioned in a highly conductive
environment and receives radiation from an external target through
a tube. Electronics determine the target temperature based on the
sensor output signal and a temperature sensor signal.
Inventors: |
Pompei, Francesco; (Boston,
MA) |
Correspondence
Address: |
HAMILTON, BROOK, SMITH & REYNOLDS, P.C.
530 VIRGINIA ROAD
P.O. BOX 9133
CONCORD
MA
01742-9133
US
|
Assignee: |
Exergen Corporation
Watertown
MA
|
Family ID: |
27569568 |
Appl. No.: |
10/667135 |
Filed: |
September 19, 2003 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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10667135 |
Sep 19, 2003 |
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10390532 |
Mar 14, 2003 |
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10390532 |
Mar 14, 2003 |
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09808619 |
Mar 14, 2001 |
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09808619 |
Mar 14, 2001 |
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09293477 |
Apr 16, 1999 |
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6219573 |
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09293477 |
Apr 16, 1999 |
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08682260 |
Jul 17, 1996 |
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6047205 |
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08682260 |
Jul 17, 1996 |
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08333205 |
Nov 2, 1994 |
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5653238 |
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08333205 |
Nov 2, 1994 |
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07832109 |
Feb 6, 1992 |
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5325863 |
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08333205 |
Nov 2, 1994 |
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07889052 |
May 22, 1992 |
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5381796 |
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08333205 |
Nov 2, 1994 |
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07760006 |
Sep 13, 1991 |
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5445158 |
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07760006 |
Sep 13, 1991 |
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07646855 |
Jan 28, 1991 |
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5199436 |
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07646855 |
Jan 28, 1991 |
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07338968 |
Apr 14, 1989 |
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5012813 |
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07338968 |
Apr 14, 1989 |
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07280546 |
Dec 6, 1988 |
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4993419 |
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Current U.S.
Class: |
600/549 ;
374/E1.013; 374/E13.003 |
Current CPC
Class: |
G01J 5/041 20130101;
G01J 5/06 20130101; G01J 5/07 20220101; G01J 5/021 20130101; G01J
5/026 20130101; G01J 5/025 20130101; G01J 5/14 20130101; G01J 5/03
20220101; G01J 5/046 20130101; G01J 5/0818 20130101; G01J 5/02
20130101; G01K 13/223 20210101; G01J 5/045 20130101; G01J 5/064
20220101; G01J 5/049 20130101; G01J 5/08 20130101; G01J 5/16
20130101; G01J 5/04 20130101; G01J 5/047 20130101 |
Class at
Publication: |
600/549 |
International
Class: |
A61B 005/00 |
Claims
What is claimed is:
1. A temperature detector comprising: a surface temperature sensor
mounted to sense temperature of a target surface; an ambient
temperature sensor sensing ambient temperature; an electronic
circuit coupled to the surface temperature sensor and ambient
temperature sensor and responsive to a signal from the surface
temperature sensor and the ambient temperature sensed by the
ambient temperature sensor to provide an indication of an internal
temperature of the target adjusted for the ambient temperature to
which the target is exposed; and an output providing an indication
of the internal temperature.
2. A temperature detector as claimed in claim 1 wherein the target
surface is biological tissue.
Description
RELATED APPLICATIONS
[0001] This application is a Continuation of application Ser. No.
10/390,532, filed on Mar. 14, 2003, which is a Continuation of
application Ser. No. 09/808,619, filed on Mar. 14, 2001, which is a
Continuation of application Ser. No. 09/293,477, filed Apr. 16,
1999, which is a Continuation of Ser. No. 08/682,260, filed Jul.
17, 1996, which is a Continuation of Ser. No. 08/333,205, filed
Nov. 2, 1994, now U.S. Pat. No. 5,653,238, which is a
Continuation-in-part of application Ser. No. 07/832,109, filed Feb.
6, 1992, now U.S. Pat. No. 5,325,863 and of application Ser. No.
07/889,052, filed May 22, 1992, now U.S. Pat. No. 5,381,796 and of
application Ser. No. 07/760,006, filed Sep. 13, 1991, now U.S. Pat.
No. 5,445,158, which is a Continuation-in-Part of application Ser.
No. 07/646,855, filed Jan. 28, 1991, now U.S. Pat. No. 5,199,436,
which is a Divisional of application Ser. No. 07/338,968, filed
Apr. 14, 1989, now U.S. Pat. No. 5,012,813, which is a
Continuation-in-part of application Ser. No. 07/280,546, filed Dec.
6, 1988, now U.S. Pat. No. 4,993,419.
[0002] The entire teachings of the above applications are
incorporated herein by reference.
BACKGROUND OF THE INVENTION
[0003] Radiation detectors which utilize thermopiles to detect the
heat flux from target surfaces have been used in various
applications. An indication of the temperature of a target surface
may be provided as a function of the measured heat flux. One such
application is the testing of electrical equipment. Another
application has been in the scanning of cutaneous tissue to locate
injured subcutaneous regions. An injury results in increased blood
flow which in turn results in a higher surface temperature. Yet
another application is that of ear temperature measurement. More
specifically, a tympanic device relies on a measurement of the
temperature of the tympanic membrane area in the ear of an animal
or human by detection of infrared radiation as an alternative to
traditional sublingual thermometers. Other ear temperature
measurements may be limited to the outer region of the ear
canal.
SUMMARY OF THE INVENTION
[0004] In one embodiment of the present invention, a radiation
detector comprises a radiation sensor such as a thermopile and a
thermal mass enclosing the thermopile. The thermal mass includes an
elongated thermally conductive tube of a first internal diameter.
The tube extends from the distal end of the detector to a rear
volume of larger internal diameter in which the sensor is mounted.
In one device, the tube is gold plated and is thus highly
reflective. In another device the tube is plated with a metal oxide
for high absorption of radiation. A rigid window is mounted
adjacent to an end of the tube, preferably the distal end where it
seals the tube.
[0005] In accordance with one feature of the present invention, the
portions of the thermal mass forming the tube and rear volume are
formed in a unitary structure of high thermal conductivity
material. The unitary thermal structure has an outer surface with
an outer diameter at its distal end which is less than an outer
diameter about the rear volume. The outer surface is tapered about
the tube such that a unitary thermal mass of increasing outer
diameter is provided about the end of the tube adjacent to the rear
volume. The unitary thermal mass maximizes conductance and thermal
mass within a limited diameter. To avoid changes in fixtures used
in mounting the thermopile within the unitary thermal structure, in
one embodiment the thermal structure is of limited diameter and may
be supplemented with an additional thermal mass. The additional
thermal mass surrounds the rear volume and a portion of the tube
and is in close thermal contact with the unitary thermal structure.
In another embodiment, the unitary thermal structure extends from
the distal end of the detector to a housing such that no additional
thermal mass is required.
[0006] It has been found that a narrow field of view radiation
detector provides a more accurate and reliable reading of tympanic
temperature. In the detector of the present invention, that field
of view is obtained by controlling the reflectance of the inner
surface of the tube, the length and diameter of the tube and the
position of the thermopile behind the tube. In one embodiment, the
tube has a reflective inner surface providing a field of view from
the thermopile of about sixty degrees or less. A field of view of
less than about sixty degrees allows for viewing of only a portion
of the ear canal within less than about 1 centimeter of the
tympanic membrane. In another embodiment, the tube has a
nonreflective inner surface which produces a field of view from the
thermopile of about thirty degrees or less. In either embodiment,
the thermopile response may be fine tuned by changing the position
of the thermopile behind the tube which changes the field of view
and alters the thermopile response signal level.
[0007] In accordance with another aspect of the present invention,
the infrared radiation sensor is mounted in the rear volume within
the unitary thermal mass. The sensor has an active area influenced
by radiation from an external target and a reference area of known
temperature which is substantially unaffected by radiation. The
sensor is preferably a thermopile having its cold junction
reference area thermally coupled to the thermal mass but it may be
a pyroelectric device. The thermally conductive tube is thermally
coupled to the thermal mass and passes radiation to the sensor from
the external target. A thermal barrier surrounds the thermal mass
and tube. The temperature of the thermal mass, and thus of the
sensor reference area, is allowed to float with ambient. A
temperature measurement of the thermal mass is made to compensate
the sensor output.
[0008] Temperature differences between the tube and sensor
reference area would lead to inaccurate readings. To avoid those
differences, the large unitary thermal mass minimizes temperature
changes from heat which passes through the thermal barrier, and
good conductivity within the mass increases conductance and
minimizes temperature gradients. The outer thermal RC time constant
for thermal conduction through the thermal barrier to the thermal
mass and tube is at least two, and preferably at least three orders
of magnitude greater than the inner thermal RC time constant for
the temperature response of the reference area to heat transferred
to the tube and thermal mass. For prompt readings, the inner RC
time constant should be about 1/2 second or less.
[0009] Preferably, the thermally conductive tube is thermally
coupled to the sensor by a thermally conductive material such as
epoxy. In accordance with the present invention, the amount of
thermally conductive material is tuned to the detector to minimize
the response of the sensor to undesired thermal perturbations of
the tube. Providing an insufficient amount of material causes a
positive error response from the sensor for thermal perturbations,
while too much material causes a negative error response from the
sensor for thermal perturbations. By providing the proper amount of
material between the sensor and the tube, the added thermal
conductance from the material tunes the reference area and the
active area of the sensor to respond in phase to thermal
perturbations such that the sensor response is substantially
unaffected by said perturbations.
[0010] In the radiation detector of the present invention, the
radiation sensor and the tube are positioned in an extension which
is particularly suited for obtaining tympanic temperature
measurements. To accomplish this, the extension is inserted into a
subject's ear, and preferably into the ear canal. Once inserted,
the extension is pivoted and the sensor scans the ear canal and
senses the emitted radiation. The detector employs electronics
which detects the peak radiation sensed by the sensor and converts
it to a tympanic temperature indication.
[0011] The probe extension which supports the radiation sensor
extends from a housing which displays the tympanic temperature. The
housing extends along a first axis and the extension preferably
extends at an angle of about 75 degrees from the first axis. This
housing supports the battery powered electronics for converting
radiation sensed by the sensor to tympanic temperature displayed by
the display. The electronics included a processor for providing the
displayed temperature based on radiation received from the tympanic
membrane. If the sensor receives radiation from the cooler outer
ear instead of the tympanic membrane, the processor determines the
displayed temperature as a function of the received radiation
compensated by an indication of ambient temperature to produce a
core temperature approximation. The entire instrument is housed in
a single hand-held package. The small additional weight of the
electronics in the hand-held unit is acceptable because readings
can be made quickly.
[0012] In accordance with another aspect of the present invention,
the probe extension is adapted to be inserted into an ear canal.
More specifically, the diameter of the distal tip as well as the
shape and taper of the extension may be set to provide a detector
useful in normal adult ear canals or a pediatric detector useful in
small ear canals, especially children's ear canals, and swollen
adult ear canals. To that end, the extension has a diameter of
about 3-8 mm about its distal end and a substantially conical shape
increasing in diameter along its length from its distal end and
characterized by an included angle of about 25-60 degrees. As such,
the extension is capable of being inserted into an ear canal up to
one-third of the length of the ear canal.
[0013] In a pediatric detector embodiment the conical shape of the
extension has an included angle of about forty degrees. Further,
the diameter of the tip of the distal end of the extension is
preferably in the range of 3-6 min. As such, the pediatric detector
is particularly useful on subjects having small ear canals but is
also useful on adult subjects. In another embodiment the conical
portion of the extension has an included angle of about thirty
degrees. The diameter of the tip of the distal end of the extension
is no more than about 7 min. As such, the detector is particularly
useful on adult subjects having normal ear canals, but it may also
be used on children.
[0014] The radiation sensor assembly of a preferred embodiment
includes a sensing device which is mounted within a rigid structure
of high thermal conductivity such as beryllium oxide and has its
reference area thermally coupled thereto. The passage through a
thermally conductive tube passes thermal radiation from the
external target, such as a tympanic membrane, to the thermopile. A
window is mounted on the rigid structure such that it is in close
thermal contact with the structure.
[0015] In one embodiment of the present invention, a detector
comprises a substantially conical extension employing the
above-described radiation sensor assembly. Preferably, the sensor
assembly includes a thermopile sensor. In this embodiment, the tube
provides a field of view from the thermopile of about thirty
degrees or less. A thermal mass of high thermal conductivity
material surrounds the tube and encloses the rigid structure in a
rear volume. The thermal mass has a region within the rear volume
which is defined between a rearwardly facing surface of the thermal
mass and forward a face of the window. The region is preferably
filled with air, providing a low thermal conductivity environment
therein. The high thermal conductivity mass provides close thermal
contact among the tube, the rigid structure, the thermopile cold
junction and the ends of the window. As such, a continuous low
thermal resistance path is formed from the tube to the cold
junction of the thermopile and the window is held to the cold
junction temperature.
BRIEF DESCRIPTION OF THE DRAWINGS
[0016] The foregoing and other objects, features and advantages of
the invention will be apparent from the following more particular
description of preferred embodiments of the invention, as
illustrated in the accompanying drawings in which like reference
characters refer to the same parts throughout the different views.
The drawings are not necessarily to scale, emphasis instead being
placed upon illustrating the principles of the invention.
[0017] FIG. 1 illustrates one embodiment of a radiation detector
for tympanic temperature measurements in accordance with the
present invention.
[0018] FIG. 2 is a cross-sectional view of the extension of the
detector of FIG. 1 in which the thermopile radiation sensor is
positioned.
[0019] FIG. 3 illustrates another embodiment of the radiation
detector for tympanic temperature measurements in accordance with
the present invention.
[0020] FIG. 4 is a cross-sectional view of the extension of the
detector of FIG. 3 in which the thermopile radiation sensor is
positioned.
[0021] FIG. 5 is a profile of pair of configurations of the
extension of FIG. 4.
[0022] FIG. 6 is an enlarged cross-sectional view of the extension
of FIG. 4.
[0023] FIG. 7 is a cross-sectional view of a radiation sensor
assembly of the detector of FIG. 6
[0024] FIG. 8 is a block diagram of the electronic circuit of the
detector of the present invention.
[0025] FIGS. 9A-9D are flow charts of the system firmware.
[0026] FIG. 10 is a cross-sectional view of a thermopile can
embodying a feature of the present invention.
DETAILED DESCRIPTION OF THE INVENTION
[0027] A description of preferred embodiments of the invention
follows.
[0028] In one embodiment of the present invention, the radiation
detector 12 of FIG. 1 includes a flat housing 14 with a digital
display 16 for displaying a tympanic temperature measurement.
Although the display may be located anywhere on the housing, it is
preferred that it be positioned on the end so the user is not
inclined to watch it during a measurement. The instrument makes an
accurate measurement when pivoted to scan the ear canal, and the
user should concentrate on only the scanning motion. Then the
display can be read. A thermopile radiation sensor is supported
within a probe 18 at the opposite end of the housing 14. The
housing extends along a first axis 19 (FIG. 2) and the extension 18
extends orthogonally from an intermediate extension 20 which
extends at an angle of about 15 degrees from the first axis. As
such, the extension 18 extends at an angle of about 75 degrees from
the first axis 19 of the housing. Thus, the head of the detector,
including the extension 18 and 20, has the appearance of a
conventional otoscope. An on/off switch 22 is positioned on the
housing.
[0029] A cross-sectional view of the extension of the detector of
FIG. 1 is illustrated in FIG. 2. A base portion 23 is positioned
within the housing 14, and the housing clamps about a groove 24. As
noted, the portion 20 extends at about a 15 degree angle from the
first axis 19 and thus from the base portion 23. Further, the
extension 18 extends at about a 75 degree angle from the first
axis. The extension 18 is tapered toward its distal end at 26 so
that it may be comfortably positioned in the ear canal to view the
tympanic membrane and/or ear canal.
[0030] A preferred disposable element to be used over the extension
18 is presented in the '419 patent and will not be discussed
here.
[0031] The edge at the end of the probe is rounded so that when the
probe is inserted into the ear it can be pivoted somewhat without
discomfort to the patient. The probe is also curved like an
otoscope to avoid interference with the ear. By thus pivoting the
probe, the ear canal is scanned and, at some orientation of the
probe during that scan, one can be assured that the maximum
temperature is viewed. Since the ear canal cavity leading to the
tympanic area is the area of highest temperature, the instrument is
set in a peak detection mode, and the peak detected during the scan
is taken as the tympanic temperature.
[0032] An improved assembly within the extension 18 is illustrated
in FIG. 2. A thermopile 28 is positioned within a can 30 of high
conductivity material such as copper. The conductivity should be
greater than two watts per centimeter per degree Kelvin. The can is
filled with a gas of low thermal conductivity such as Xenon. The
thermopile 28 is positioned within a rear volume 31. It is mounted
to an assembly which includes a header 33. The volume is sealed by
cold welding of the header 33 to a flange 42 extending from the
can. Cold welding is the preferred approach to making the seal and,
to utilize past welding fixtures, the outer diameter of the can is
limited. Thermal epoxy may be used as an alternative.
[0033] The thermopile views the tympanic membrane area through a
radiation guide 32. The radiation guide 32 is gold plated to
minimize oxidation. It is closed at its forward end by a germanium
window 35. The rigid germanium window assures that the radiation
guide is sealed from contamination and is itself easily cleaned.
Germanium is less fragile than silicon and passes higher
wavelengths. To minimize expense, the window is square with each
side slightly longer than the diameter of the radiation guide 32.
The window is cemented with epoxy within a counterbore in a flange
37 at the end of the radiation guide. The epoxy serves as a gas
seal and mechanical support for the somewhat brittle germanium
window. The flange serves to protect the germanium window should
the detector be dropped. The diagonal of the window is less than
the diameter of the counterbore, and its thickness is less than the
depth of the counterbore. Therefore, if the detector is dropped,
any force which presses the plastic housing toward the window is
absorbed by the flange. The germanium need only withstand the
forces due to its own inertia.
[0034] From the perspective of the thermopile flake 28, the
radiation guide 32 shifts the front aperture at the window 35 back
to the proximal end of the radiation guide at 46. Thus, the field
of view of the device is determined by the diameter of the aperture
46 and its distance from the flake 28. There are, however, stray
rays which, though not being directed to the flake from the
aperture, may ultimately strike the flake after reflection within
the volume at 31. Such reflections effectively increase the field
of view and are thus undesirable. The frustoconical surface 44
surrounding the aperture 46 reflects most of those stray rays
toward the rear of the volume 31 rather than toward the thermopile
flake. As shown in FIG. 2, the flake views itself in the surface
44, thus minimizing stray radiation.
[0035] The angled surface surrounding the aperture can be applied
to more conventional thermopile cans as illustrated in FIG. 10.
Here, the window 310 is mounted directly across the aperture 312 of
the can 314. As in conventional assemblies, the can is closed by
rear header 316. The thermopile flake 318 is centered on a
polyester sheet 320 stretched between beryllium oxide rings 322 and
324. As in the case of FIG. 2, the surface 326 surrounding the
aperture 312 is frustoconical such that it is angled back from the
aperture. It can be seen that stray rays 328 which should not be
seen by the thermopile flake 318 will be reflected rearwardly
toward the beryllium oxide rings here they should be absorbed
rather than toward the flake as indicated by the broken lines as
they would if the surface surrounding the aperture were
cylindrical.
[0036] Whereas the detector disclosed in the '419 patent had a
field of view of about 120.degree., it has been determined that a
narrower field of view of about sixty degrees or less provides the
user with an easier and more accurate indication of tympanic
temperature. With a narrower field of view, the thermopile flake,
when directly viewing the tympanic membrane, also views less than
about one centimeter along the ear canal wherein the tissue is at
substantially the same temperature as the tympanic membrane. A
better view of the tympanic membrane also results from the
cylindrical extension 43 beyond the conical portion of the
extension 18. With the ear canal straightened by the probe, the
extension 43 can extend well into the ear canal beyond any hair at
the canal opening.
[0037] The tympanic membrane is about 2.5 centimeters from the
opening of the ear canal. The ear canal for an adult subject is
typically about 8 mm wide, so the diameter of the tip of the
extension is no more than about 8 mm wide. The conical portion of
the extension 18 prevents the tip of the extension from extending
more than about eight millimeters into the ear canal. Beyond that
depth, the patient suffers noticeable discomfort. With a field of
view of less than about sixty degrees, the ear canal is viewed more
than about eight millimeters from the tip of the extension 18.
Thus, only the ear canal within less than 9 millimeters of the
tympanic membrane is viewed as the radiation guide is directed
toward the membrane. The result is a more accurate and reliable
reading of the tympanic temperature which is essentially core
temperature.
[0038] With the present instrument, the narrow field of view is
obtained by extending the enlarged rear volume between the flake
and the radiation guide. Radiation which enters the radiation guide
at greater angles, yet travels through the radiation guide, leaves
the guide at greater angles and is thus unlikely to be viewed by
the flake. The length of the radiation guide is another parameter
which affects the field of view. By using a planoconvex lens as the
window 35, the field of view can be further limited.
[0039] Decreasing the field of view increases the amount of heat
which is absorbed by the can in which the thermopile is mounted.
The added heat load adds to the importance that the can, including
the radiation guide, have a large thermal mass and high thermal
conductivity as discussed below.
[0040] As distinguished from the structure presented in the '419
patent, the volume 31 surrounding the thermopile and the radiation
guide are formed of a single piece of high conductivity copper.
This unitary construction eliminates any thermal barriers between
the foremost end of the radiation guide and the portion of the can
surrounding the thermopile which serves as the cold junction of the
thermopile. Further, at least a portion of added thermal mass which
surrounds the radiation guide is unitary with the can as well.
Specifically, a taper 39 results in an enlarged region 41 which
serves as a thermal mass in accordance with the principals of the
parent application. The taper 39 continues along a conductive
thermal mass 34 which surrounds the can and a conductive plug 36.
Both the mass 34 and plug 36 are of copper and are in close thermal
contact with the can 30.
[0041] The outer sleeve 38 of the extension 18 and the intermediate
extension 20 are of plastic material of low thermal conductivity.
The sleeve 38 is separated from the can 30 and thermal mass 34 by
an insulating air space 40. The taper of the can 30 and thermal
mass 34 permits the insulating space to the end of the extension
while minimizing the thermal resistance from the end of the tube 32
to the thermopile, a parameter discussed in detail below. The inner
surface of the plastic sleeve 38 may be coated with a good thermal
conductor to distribute across the entire sleeve any heat received
from contact with the ear. Twenty mils of copper coating would be
suitable.
[0042] In contrast with the prior design, the portion of the sleeve
38 at the foremost end of extension 18 has a region 43 of constant
outer diameter before a tapered region 45. The region of constant
outer diameter reduces the outer diameter at the distal end and
minimizes interference when pivoting the extension in the ear to
view the tympanic membrane area. The tapered region is spaced six
millimeters from the end of the extension to allow penetration of
the extension into the ear canal by no more than about eight
millimeters.
[0043] One of the design goals of the device was that it always be
in proper calibration without requiring a warm-up time. This
precluded the use of a heated target in a chopper unit or heating
of the cold junction of the thermopile as was suggested in the
O'Hara et al. U.S. Pat. No. 4,602,642. To accomplish this design
goal, it is necessary that the system be able to operate with the
thermopile at any of a wide range of ambient temperatures and that
the thermopile output have very low sensitivity to any thermal
perturbations.
[0044] The output of the thermopile is a function of the difference
in temperature between its warm junction, heated by radiation, and
its cold junction which is in close thermal contact with the can
30. In order that the hot junction respond only to radiation viewed
through the window 35, it is important that the radiation guide 32
be, throughout a measurement, at the same temperature as the cold
junction. To that end, changes in temperature in the guide 32 must
be held to a minimum, and any such changes should be distributed
rapidly to the cold junction to avoid any thermal gradients. To
minimize temperature changes, the tube 32 and the can 30 are, of
course, well insulated by means of the volume of air 40. Further, a
high conductance thermal path is provided to the cold junction.
This conductance is enhanced by the unitary construction. Further,
the can 30 is in close thermal communication with the thermal
masses 34 and 36, and the high conductivity and thickness of the
thermal masses increase the thermal conductance. A high thermal
conductivity epoxy, solder or the like joins the can and thermal
masses. The solder or epoxy provides a significant reduction in
thermal resistance. Where solder is used, to avoid damage to the
thermopile which is rated to temperatures of 125.degree. C., a low
temperature solder of indium-tin alloy which flows at 100.degree.
C. is allowed to flow into the annular mass 34 to provide good
thermal coupling between all elements.
[0045] The thermal resistance from the outer surface of the plastic
sleeve 38 to the conductive thermal mass is high to minimize
thermal perturbations to the inner thermal mass. To minimize
changes in temperature of the guide 32 with any heat transfer to
the can which does occur, the thermal mass of the can 30, annular
mass 34 and plug 36 should be large. To minimize thermal gradients
where there is some temperature change in the tube during
measurement, the thermal resistance between any two points of the
thermal mass should be low.
[0046] Thus, due to the large time constant of the thermal barrier,
any external thermal disturbances, such as when the extension
contacts skin, only reach the conductive thermal mass at extremely
low levels during a measurement period of a few seconds; due to the
large thermal mass of the material in contact with the cold
junction, any such heat transfer only causes small changes in
temperature; and due to the good thermal conductance throughout the
thermal mass, any changes in temperature are distributed quickly
and are reflected in the cold junction temperature quickly so that
they do not affect temperature readings.
[0047] The thermal RC time constant for thermal conduction through
the thermal barrier to the thermal mass and tube should be at least
two orders of magnitude greater than the thermal RC time constant
for the temperature response of the cold junction to heat
transferred to the tube and thermal mass. The RC time constant for
conduction through the thermal barrier is made large by the large
thermal resistance through the thermal barrier and by the large
thermal capacitance of the thermal mass. The RC time constant for
response of the cold junction is made low by the low resistance
path to the cold junction through the highly conductive copper can
and thermal mass, and the low thermal capacitance of the stack of
beryllium oxide rings and pin conductors to the thermopile.
[0048] Although the cold junction capacitance is naturally low,
there are size constraints in optimizing the thermal capacitance of
the thermal mass, the thermal resistance through the thermal
barrier and the internal thermal resistance. Specifically, the
external thermal resistance can be increased by increased radial
dimensions, the capacitance of the thermal mass can be increased by
increasing its size, and the thermal resistance through the
longitudinal thermal path through the tube can be decreased by
increasing its size. On the other hand, the size must be limited to
permit the extension to be readily positioned and manipulated
within the ear.
[0049] Besides the transfer of heat from the environment, another
significant heat flow path to the conductive thermal mass is
through leads to the system. To minimize heat transfer through that
path, the leads are kept to small diameters. Further, they are
embedded in the plug 36 through bores 70; thus, any heat brought
into the system through those leads is quickly distributed
throughout the thermal mass, and only small changes in temperature
and small gradients result.
[0050] Because the temperature of the thermal mass is not
controlled, and the response of the thermopile 28 is a function of
its cold junction temperature, the cold junction temperature must
be monitored. To that end, a thermistor is positioned at the end of
a central bore 72 in the plug 36.
[0051] Another embodiment of the present invention is illustrated
in FIG. 3. The radiation detector 212 employs a thermopile
radiation sensor supported within a probe extension 218 of the
opposite end of the housing 14. As shown in FIG. 4, the extension
218 extends at an angle of about 75 degrees from a first axis 219
along which the housing extends. The extension 218 is tapered along
its length from its distal end, making the instrument 212
particularly useful in obtaining tympanic temperature measurements
without causing the subject discomfort.
[0052] As previously discussed, the other embodiment provided an
extension with a constant diameter tip which works well in ear
canals of about the same diameter. However, this tip does not fit
within smaller ear canals, and subjects with larger diameter ear
canals will suffer discomfort as the constant diameter tip of the
extension contacts the walls of their ear canals during pivoting to
scan the ear canal. In accordance with the present invention, the
substantially conical shaped extension 218 has an increasing
diameter along a portion of its length from its distal end such
that the extension may be inserted into an ear canal without
causing discomfort. Once inserted, the extension 218 is pivoted to
scan the ear canal adjacent to and including the tympanic membrane.
The conical shape of the extension 218 ensures that the edge of the
tip of the extension is unable to contact the walls of the ear
canal. The thermopile 28 senses radiation within the ear canal
during the pivotal rotation of the extension 218. The detector 212
employs electronics in the housing 14 for detecting the peak
radiation sensed by the sensor 28 and converting it to a tympanic
temperature indication. Further, the electronics may also provide
an audible tone indicating that peak radiation has been detected
for a particular measurement period. The variable tone or variable
pulse signal allows a user to know when to stop pivoting the
extension for a given subject.
[0053] The diameter of the distal tip of the probe extension as
well as its taper may be selected to provide a detector useful in
normal ear canals or a pediatric detector useful in small ear
canals. In one configuration, as shown in FIG. 5, the extension 218
has a small diameter tip and is tapered along its length at its
distal end making the extension particularly suited for insertion
into small ear canals. A small ear canal is about 3-6 mm wide, so
the diameter of the extension 218 along the portion of its length
from its distal tip 226 is no more than about 3-6 mm. Further, the
extension 218 comprises an outer sleeve 238 with a tapered portion
245 extending at a twenty degree angle from the distal tip 226. As
such, the conical portion 245 of the extension has an included
angle of about forty degrees. With a preferred 3.4 mm outer
diameter at the tip 226 and a forty degree included angle along the
conical portion 245, the extension 218 is capable of being inserted
about 4 mm into a small ear canal. A young child's ear canal is
about 10 mm in length, so the extension may be inserted into the
child's ear canal up to about one-third of the length of the ear
canal without causing discomfort.
[0054] In another configuration, indicated by dashed lines in FIG.
5, an extension 318 has a larger diameter tip and is tapered such
that the extension is particularly suited for normal ear canals
including adult ear canals and ear canals of older children. A
normal ear canal is about 8 mm wide, and the diameter of the
extension 318 about its distal tip 326 is no more than 7 mm. The
tapered portion 345 of the outer sleeve extends at about a fifteen
degree angle from the distal tip 326 which corresponds to a thirty
degree included angle. As such, the extension 318 having a
preferred tip diameter of about 5 mm is capable of being inserted
about 8 mm into a normal ear canal, or about one-third of the
length into the canal without causing the subject discomfort.
[0055] Referring to FIG. 5, the extensions 218 and 318 have
different profiles which were selected to minimize discomfort to
the subject and to provide for accurate tympanic temperature
readings. To that end, the diameter of the tip of the extensions is
specified and depends on the diameter of the subject's ear canal.
Further, the extensions are configured to provide a field of view
of about thirty degrees which provides more accurate readings as
explained below. Thus, to provide a thirty degree field of view at
.theta..sub.1, with a 3 mm inner diameter of tube 232, the length
21 from the tip 226 to the thermopile 28 is about 7.5 mm. Due to
the proximity of the thermopile 28 to the tip (7.5 mm), the
extension 218 requires the steeper taper of 20 degrees so that the
thermopile assembly (not shown) fits into the extension. Also, the
taper of 20 degrees provides a necessary stop in close proximity to
the distal end 226 for preventing insertion of the extension 218
too far into a short ear canal so as to cause discomfort. To
achieve the thirty degree field of view at .theta..sub.2 with a
tube 322 diameter of about 4.5 mm, a length of L2 of about 11 mm is
required. Due to the larger diameter tip 326, the thermopile 328 is
further from the tip for the same field of view so that the conical
portion 345 may have a 15 degree taper. An adult canal has a flap
of cartilage at the outer region of the ear (the concha). Thus, the
conical portion 345 having the 15 degree taper is advantageous as
it allows the extension 318 to be narrower and thus be inserted
past the cartilage and extend into the ear canal.
[0056] An improved assembly within the extension 218 is shown in
FIG. 4. A thermopile 28 is positioned within a thermal mass 230
formed of high thermal conductivity material such as copper. In
contrast to the previous embodiment, the thermal mass 230 is a
one-piece structure which mounts into a bore 233 within a portion
220 of the extension 218. Further, no contact between the thermal
mass 230 and the outer sleeve 238 is made at the distal end 226 of
the extension. Instead, a ridge 242 in the mass 230 contacts the
sleeve 238 to achieve alignment of the mass and the distal end of
the sleeve. The thermopile 28 is located in a rear volume 231 and
views the tympanic membrane area through a conductive tube 232
formed in the mass 230.
[0057] Referring to FIGS. 6 and 7, the thermopile is mounted on the
rear surface of a sheet of polytetrafluoroethylene 248 suspended
from the rear surface of a first beryllium oxide ring 250. A mass
of infrared absorbing black material 258 is positioned on the
opposite surface of the sheet and serves as a radiation collector.
A second beryllium oxide ring 252 supports the first ring 250 and
the two rings are supported by a copper header 256. A window 235
formed of silicon or germanium is mounted on the first ring 250.
The rings 250 and 252, the window 235 and the header 256 are
thermally coupled by high thermal conductivity epoxy 255. A pair of
leads 260 formed of 20 mils of kovar provide structural support to
the assembly and provide a thermopile output signal to the
electronics via a pair of 40 gauge wires 262. As such, the tube and
the region defined by the surface 237 and the window 235 are filled
with air. A sufficient amount of silver paint may be included
within the rings to oxidize all air, and thus create a nitrogen
environment in the gas tight region. Alternatively, the window may
be positioned at the distal end 226 of the housing 218 as indicated
by the dashed lines in FIG. 4. Having the window positioned
directly on the sensor assembly minimizes temperature gradients
between the window and thermopile, but positioning the window at
the distal end minimizes contamination of the surface of tube
232.
[0058] It has been determined that a significantly narrower field
of view provides the user with an easier and more accurate tympanic
temperature indications. The detector disclosed in the '419 patent
had a wide field of view of about 120.degree. and the detectors
disclosed in the '813 patent and described in the other embodiment
have a field of view of about 60.degree. or less. Thus, one object
of this embodiment was to reduce the field of view to obtain a
narrower field of view of about thirty degrees or less. To that
end, the narrower field of view is obtained by plating the inner
surface of the tube 232 with a layer of non-reflective material.
Preferably, the non-reflective layer is a metal oxide such as
nickel oxide or aluminum oxide. A metal oxide layer is employed
because metal oxides are durable and will not change in properties
if the inner surface of the tube is cleaned. Further, the metal
oxide layer should be thin (a few tenths of thousandths of an inch)
such that virtually no temperature gradient exists across the
layer. The metal oxide surface absorbs substantially all radiation
which strikes the tube 232 and allows radiation passing directly
through the tube to reach the thermopile 28.
[0059] The dimensions of the tube 232 are chosen such that
radiation entering the tube at angles of only up to fifteen degrees
from the longitudinal axis of the tube passes directly to the
thermopile. With the thirty degree field of view, the probe can
easily be positioned such that substantially only the tympanic
membrane may be viewed.
[0060] The above approach to decreasing the radiation gathering
aperture size to about 3 mm and reducing the field of view to about
thirty degrees significantly increases the noise level at the
thermopile relative to the signal level. Further, this approach
increases the amount of radiation which is absorbed by the thermal
mass in which the thermopile is mounted. These two effects add to
the importance that the thermal mass, including the tube, provide a
large thermal mass and high thermal conductivity.
[0061] The thermal mass 230 is of unitary construction which
eliminates thermal barriers between the tube 232 and the portion
241 of the thermal mass surrounding the thermopile 28. Further, a
plug 272 of high thermal conductivity material positioned behind
the thermopile 28 is in close thermal contact with the mass 230.
The outer sleeve 238 is formed of low thermal conductivity plastic
and is separated from the mass 230 by an insulating air space 240.
The taper 239 of the mass 230 increases the insulating air space
adjacent to the end of the extension 226 while minimizing thermal
resistance from the tube 232 to the thermopile. The inner surface
of the plastic sleeve 238 may be coated with a good thermal
conductor to distribute across the entire sleeve any heat received
from contact with the ear.
[0062] In order that the hot junction respond only to radiation
viewed through the window 235, it is important that the tube 232
and the window 235 be, throughout a measurement, at the same
temperature as the cold junction. The thermopile 28 acts as a
thermal amplifier having a gain based on the number of junctions
and the Seebeck coefficient. Thus, temperature gradients sensed by
the thermopile are amplified by a factor of about 100. To minimize
errors, changes in temperature in the tube 232 must be held to a
minimum, and any such changes should be distributed rapidly to the
cold junction to avoid any thermal gradients. To minimize
temperature changes, the tube 232 and the mass 230 are well
insulated by means of the volume of air 240. To avoid thermal
gradients, the tube 232 is plated with a thin layer of high
conductance non-reflectance metal oxide which minimizes temperature
gradients across the layer. Further, the thermal mass 230 is
thermally coupled to the rings 250 and 252 with high conductivity
thermal epoxy 255 such that a high conductance thermal path is
provided from the tube 232 to the cold junction. This conductance
is enhanced by the unitary construction of the mass 230.
[0063] In accordance with another aspect of the invention, the
amount of thermal epoxy 255 between the rings 250 and 252 and the
mass 230 is tuned to the assembly to minimize the response of the
thermopile 28 to undesired thermal perturbations at the end of the
mass. Referring to FIG. 6, thermal variations in the air region 243
lead to heating of the tip 227 of the mass 230 which causes the
inner surface of the tube 232 to emit radiation. If these thermal
variations are not sensed by the cold junction via the high
conductance thermal path from the tube 232 in phase with the
sensing of the radiation by the hot junction, the thermopile 28
produces an error response.
[0064] Accordingly, the epoxy 255 may be incrementally added to
adjust the high conductivity thermal path to the cold junction to
bring the hot and cold junction thermal responses in phase. An
insufficient amount of epoxy 255 causes a positive error response
as the hot junction responds to thermal variations faster than the
cold junction. Alternatively, too much epoxy 255 causes a negative
error response as the cold junction responds faster to thermal
variations than the hot junction. When the proper amount of epoxy
has been provided, the tuned assembly produces no more than
0.1.degree. thermopile response for up to 20.degree. thermal
variations during a test.
[0065] It has been determined in previous devices that a
significant source of thermal gradients is caused by radiation from
the window. To minimize these thermal gradients, the window 235 is
mounted on the ring 250 with high thermal conductivity epoxy 255
such that it is thermally coupled to the cold junction. The epoxy
provides a significant reduction in thermal resistance and provides
good thermal coupling between all elements. On the other hand,
conductance to the viewing region of the window should not be less
than that to the cold junction. Thus, the window 235 is spaced from
a rear face 237 of the mass 230 and its ends are spaced from the
inner volume 231 by a low thermal conductivity air region. The
region ensures that temperature gradients are distributed to the
cold junction via the thermal mass and not directly through the
window causing thermal gradients.
[0066] The thermal resistance from the outer surface of the plastic
sleeve 238 to the conductive thermal mass 230 is high to minimize
thermal perturbations to the inner thermal mass. The thermal mass
is large to minimize changes in temperature of the tube 232 with
any heat transfer to the mass which does occur. Further, the
thermal resistance between any two points of the thermal mass 230,
the tube 232, the window 235 or the rings 250 and 252 is low to
minimize thermal gradients where there is some temperature change
in the tube during measurement.
[0067] Thus, due to the large time constant of the thermal barrier
238, any external thermal disturbances, such as when the extension
contacts skin, only reach the conductive thermal mass 230 at
extremely low levels during a measurement period of a few seconds.
Due to the large thermal mass of the materials in contact with the
cold junction, any such heat transfer only causes small changes in
temperature. Also, due to the good thermal conductance throughout
the thermal mass, tube, window and rings any changes in temperature
are distributed quickly and are reflected in the cold junction
temperature quickly so that they do not affect temperature
readings.
[0068] The thermal RC time constant for thermal conduction through
the thermal barrier 238 to the thermal mass 230 and tube 232 is at
least two orders of magnitude greater than the thermal RC time
constant for the temperature response of the cold junction to heat
transferred to the tube and thermal mass. The RC time constant for
conduction through the thermal barrier 238 is made large by the
large thermal resistance through the thermal barrier and by the
large thermal capacitance of the thermal mass. The RC time constant
for response of the cold junction is made low by the low resistance
path to the cold junction through the highly conductive thermal
mass, and the low thermal capacitance of the stack of beryllium
oxide rings to the thermopile.
[0069] Besides the transfer of heat from the environment, another
significant heat flow path in the system is through the leads 260.
To minimize heat transfer through that path, the lead diameters are
kept small and the leads 260 are trimmed off in the region 246. A
pair of 40 gauge wires 262 are soldered to the shortened leads 260.
The wires 262 extend from the region 246 through the plug 272 and
provide thermopile signals to the electronics.
[0070] Yet another potential heat flow path in the system is
through the header 256 to the plug 272. Since the header is in
close thermal contact with the thermopile cold junction, any
thermal gradients through the header 256 would be amplified 100 to
1000 times by the thermopile producing large error signals. In the
present invention, the insulating region 246 of air is provided
behind the header 256 to minimize heat transfer through that path.
Thus, any thermal gradients in the plug would be forced to travel
through the mass 230 and would be substantially dissipated without
affecting the thermopile.
[0071] Because the temperature of the thermal mass 230 is not
controlled and the response of the thermopile 28 is a function of
its cold junction temperature, the cold junction temperature must
be monitored. To that end, a thermistor 271 is positioned adjacent
to the region 246 in the plug 272. The plug 272 is in thermal
contact with the mass 230 such that the thermistor 271 is thermally
coupled to the cold junction of the thermopile 28. However, the
thermal path between the thermopile 28 and the thermistor has some
thermal resistance. This resistance produces a temperature
difference between the cold junction temperature and the sensed
temperature which is not amplified. Therefore such error is not as
significant as gradient errors amplified by the thermopile.
[0072] A schematic illustration of the electronics in the housing
14 of both embodiments of the present invention (FIGS. 1 and 3),
for providing a temperature readout on display 16 in response to
the signal from the thermopile, is presented in FIG. 8. The system
is based on a microprocessor 73 which processes software routines
included in read only memory within the processor chip. The
processor may be a 6805 processor sold by Motorola.
[0073] The voltage generated across the thermopile 28 due to a
temperature differential between the hot and cold junctions is
amplified in an operational amplifier 74. For the detector of FIG.
1, the chopper circuit 67 is not employed and analog output from
the amplifier 74 is applied as one input to a multiplexer 76. For
the detector of FIG. 3, the thermopile output voltage is smaller so
the amplifier 74 is configured in the chopper stabilized amplifier
circuit 67. The circuit employs a switched feedback loop that
removes internal offset voltages associated with the amplifier 74.
The feedback loop comprises switches 69 and 71, an amplifier 73 and
a storage capacitor C11. When the radiation detector is powered on,
switch 69 is opened and switch 71 is closed. With this
configuration, the feedback loop stores the offset voltage for the
amplifier 74 in capacitor C11. The switch positions are then
reversed such that the input signal to amplifier 74 is combined
with the offset stored in the capacitor C11. The combined output is
applied an input to the multiplexer 76.
[0074] Another input to the multiplexer 76 is a voltage taken from
a voltage divider R1, R2 which is indicative of the potential V+
from the power supply 78. A third input to the multiplexer 76 is
the potential across a thermistor RT 1 mounted in the bore 72 of
block 36. The thermistor RT 1 is coupled in a voltage divider
circuit with R3 across a reference potential VRef. The final input
to the multiplexer is a potential taken from a potentiometer R4
which may be adjusted by a user. The system may be programmed to
respond to that input in any of a number of way. In particular, the
potentiometer may be used as a gain control or as a DC offset
control.
[0075] At any time during the software routine of the
microprocessor 73, one of the four inputs may be selected by the
select lines 78. The selected analog signal is applied to a
multiple slope analog system 80 used by the microprocessor in an
integrating analog-to-digital conversion 80. The subsystem 80 may
be a TSC500A sold by Teledyne. It utilizes the reference voltage
VRef from a reference source 82. The microprocessor 73 responds to
the output from the converter 80 to generate a count indicative of
the analog input to the convertor.
[0076] The microprocessor drives four 7-segment LED displays 82 in
a multiplexed fashion. Individual displays are selected
sequentially through a column driver 84, and within each selected
display the seven segments are controlled through segment drivers
86.
[0077] When the switch 22 on the housing is pressed, it closes the
circuit from the battery 78 through resistors R5 and R6 and diode
D1 to ground. The capacitor C1 is quickly charged, and field effect
transistor T1 is turned on. Through transistor T1, the V+ potential
from the storage cell 78 is applied to a voltage regulator 86. The
regulator 86 provides the regulated +5 volts to the system. It also
provides a reset signal to the microprocessor. The reset signal is
low until the +5 volt reference is available and thus holds the
microprocessor in a reset state. When the +5 volts is available,
the reset signal goes high, and the microprocessor begins its
programmed routine.
[0078] When the switch 22 is released, it opens its circuit, but a
charge is maintained on capacitor C1 to keep transistor T1 on.
Thus, the system continues to operate. However, the capacitor C1
and transistor T1 provide a very simple watchdog circuit.
Periodically, the microprocessor applies a signal through driver 84
to the capacitor C1 to recharge the capacitor and thus keep the
transistor T1 on. If the microprocessor should fail to continue its
programmed routine, it fails to charge the capacitor C1 within a
predetermined time during which the charge on C1 leaks to a level
at which transistor T1 turns off. Thus, the microprocessor must
continue in its programmed routine or the system shuts down. This
prevents spurious readings when the processor is not operating
properly.
[0079] With transistor T1 on, the switch 22 can be used as an input
through diode D2 to the microprocessor to initiate any programmed
action of the processor.
[0080] In addition to the display, the system has a sound output 90
which is driven through the driver 84 by the microprocessor.
[0081] In order to provide an analog output from the detector, a
digital-to-analog convertor 92 is provided. When selected by line
94, the convertor converts serial data on line 96 to an analog
output made available to a user.
[0082] Both calibration and characterization data required for
processing by the microprocessor may be stored in an electrically
erasable programmable read only memory (EEPROM) 100. The EEPROM
may, for example, be a 93c46 sold by International CMOS
Technologies, Inc. The data may be stored in the EEPROM by the
microprocessor when the EEPROM is selected by line 102. Once stored
in the EEPROM, the data is retained even after power down. Thus,
though electrically programmable, once programmed the EEPROM serves
as a virtually nonvolatile memory.
[0083] Prior to shipment, the EEPROM may be programmed through the
microprocessor to store calibration data for calibrating the
thermistor and thermopile. Further, characterization data which
defines the personality of the infrared detector may be stored. For
example, the same electronics hardware, including the
microprocessor 73 and its internal program, may be used for a
tympanic temperature detector in which the output is accurate in
the target temperature range of about 60.degree. F. to a
110.degree. F. or it may be used as an industrial detector in which
the target temperature range would be from about -100.degree. F. to
5000.degree. F. Further, different modes of operation may be
programmed into the system. For example, several different uses of
the sound source 90 are available.
[0084] Proper calibration of the detector is readily determined and
the EEPROM is readily programmed by means of an optical
communication link which includes a transistor T2 associated with
the display. A communication boot may be placed over the end of the
detector during a calibration/characterization procedure. A
photodiode in the boot generates a digitally encoded optical signal
which is filtered and applied to the detector T2 to provide an
input to the microprocessor 73. In a reverse direction, the
microprocessor may communicate optically to a detector in the boot
by flashing specific segments of the digital display 82. Through
that communication link, an outside computer 106 can monitor the
outputs from the thermistor and thermopile and perform a
calibration of the devices. A unit to be calibrated is pointed at
each of two black body radiation sources while the microprocessor
73 converts the signals and sends the values to the external
computer. The computer is provided with the actual black body
temperatures and ambient temperature in the controlled environment
of the detector, computes calibration variables and returns those
variable to be stored in the detector EEPROM. Similarly, data which
characterizes a particular radiation detector may be communicated
to the microprocessor for storage in the EEPROM.
[0085] A switch 108 is positioned behind a hole 110 (FIG. 1) in the
radiation detector so that it may be actuated by a rigid metal wire
or pin. Through that switch, the user may control some specific
mode of operation such as converting the detector from degrees
Fahrenheit to degrees centigrade. That mode of operation may be
stored by the microprocessor 73 in the EEPROM so that the detector
continues to operate in a specific mode until a change is indicated
by closing the switch 108.
[0086] A switch 106 may be provided either internally or through
the housing to the user to set a mode of operation of the detector.
By positioning the switch at either the lock position, the scan
position or a neutral position, any of three modes may be selected.
The first mode is the normal scan mode where the display is updated
continuously. A second mode is a lock mode where the display locks
after a selectable delay and then remains frozen until power is
cycled or, optionally, the power-on button is pushed. The sound
source may be caused to sound at the time of lock. The third mode
is the peak mode where the display reads the maximum value found
since power-on until power is cycled or, optionally, the power-on
button is pushed.
[0087] The processor determines when the voltage from the divider
R1, R2 drops below each of two thresholds. Below the higher
threshold, the processor periodically enables the sound source to
indicate that the battery is low and should be replaced but allows
continued readout from the display. Below the lower threshold, the
processor determines that any output would be unreliable and no
longer displays temperature readings. The unit would then shut down
upon release of the power button.
[0088] In the present system, the target temperature is computed
from the relationship
T.sub.T.sup.4=Kh(H-H.sub.o)+T.sub.H.sup.4 (1)
[0089] where T.sub.T is the target temperature, Kh is a gain
calibration factor, H is the radiation sensor signal which is
offset by H.sub.o such that (H-H.sub.o)=0 when the target is at the
cold junction temperature of the device to counter any electronic
offsets in the system, and T.sub.H is the hot junction temperature.
This relationship differs from that previously used in that Kh is
temperature compensated relative to the average temperature of the
thermopile rather than the cold junction, or ambient, temperature.
Further, the hot junction temperature rather than the cold junction
temperature is referenced in the relationship.
[0090] The gain calibration factor Kh is temperature compensated by
the relationship 1 Kh = G ( 1 - Tco ( T H - T C 2 - Tz ) ) ( 2
)
[0091] where G is an empirically determined gain in the system, Tco
is the temperature coefficient of the Seebeck coefficient of the
thermopile and Tz is the temperature at which the instrument was
calibrated. The use of the average temperature of the thermopile
rather than the cold junction temperature provides for a much more
accurate response where a target temperature is significantly
different from the ambient temperature.
[0092] As noted, the relationship by which the target temperature
is determined includes the hot junction temperature as the second
term rather than the cold junction temperature. Hot junction
temperature is computed from the relationship
V.sub.s=J.alpha..sub.tav(T.sub.H-T.sub.C) (3)
[0093] where J.sub.N is the number of junctions in the thermopile
and .alpha..sub.tav is the specified Seebeck coefficient at the
average temperature of the thermopile. The Seebeck coefficient can
be determined from the relationship 2 tav = ts ( 1 - Tco ( T H - T
C 2 - T S ) ) ( 4 )
[0094] where .alpha..sub.ts is the specified Seebeck coefficient at
a particular specification temperature and T.sub.S is that
specification temperature. Again, it can be seen that temperature
compensation is based on the average thermopile temperature rather
than just the cold junction temperature. By substituting equation
(4) into equation (3) and solving for T.sub.H, the hot junction
temperature is found to be 3 t H = [ ( Tco * T S + 1 ) [ ( Tco * Ts
+ 1 ) 2 - ( 2 * Tco ) * [ ( Tco ( ( Tc * T ( Tc 2 / 2 ) ) + Tc + (
V S / J * ts ) ] ] 1 2 ] / Tco ( 5 )
[0095] The actual sensor output V.sub.S can be determined from the
digital value available to the processor from the equation: 4 V S =
( H - H 0 ) K AD G FE ( 6 )
[0096] where K.sub.AD is the analog-to-digital conversion factor in
volts/bit and G.sub.FE is the gain of the front end amplifier.
[0097] Reference to the hot junction temperature rather than the
cold junction temperature in each term of the relationship for
determining the target temperature provides for much greater
accuracy over a wide range of ambient temperatures and/or target
temperatures.
[0098] To provide a temperature readout, the microprocessor makes
the following computations: First the signal from thermistor RT1 is
converted to temperature using a linear approximation. Temperature
is defined by a set of linear equations
y=M(x-xo)+b
[0099] where x is an input and xo is an input end point of a
straight line approximation. The values of M, xo and b are stored
in the EEPROM after calibration. Thus, to obtain a temperature
reading from the thermistor, the microprocessor determines from the
values of xo the line segment in which the temperature falls and
then performs the computation for y based on the variables M and b
stored in the EEPROM.
[0100] The hot junction temperature is computed. A fourth power
representation of the hot junction temperature is then obtained by
a lookup table in the processor ROM.
[0101] The sensed radiation may be corrected using the gain
calibration factor Kh, the sensor gain temperature coefficient Tco,
the average of the hot and cold junction temperatures and a
calibration temperature Tz stored in the EEPROM. The corrected
radiation signal and the fourth power of the hot junction
temperature are summed, and the fourth root is taken. The fourth
root calculation is also based on a linear approximation which is
selected according to the temperature range of interest for a
particular unit. Again, the break points and coefficients for each
linear approximation are stored in the EEPROM and are selected as
required.
[0102] An additional facgtor based on ambient temperature may also
be included as an adjustment. The temperature of the ear T.sub.e is
sensed instead of the temperature of the tympanic membrane, the
temperature sensed by the thermopile is not actually the core
temperature T.sub.cr. There is thermal resistance between T.sub.cr
and T.sub.e. Further, there is thermal resistance between the
sensed ear temperature and the ambient temperature. The result is a
sense temperature T.sub.e which is a function of the core
temperature of interest and the ambient temperature. Based on an
assumed constant K.sub.c which is a measure of the ratio of thermal
resistances between T.sub.cr, T.sub.e and T.sub.a, T.sub.cr and
T.sub.a core temperature can be computed as 5 T cr = T a + T e - T
a k c
[0103] This computation can account for a difference of from
one-half to one degree or more between core temperature and sensed
ear temperature, depending on ambient temperature.
[0104] A similar compensation can be made in other applications.
For example, in differential cutaneous temperature scanning, the
significance of a given differential reading may be ambient
temperature dependent.
[0105] The actual computations performed by the processor are as
follows, where:
[0106] H is the digital value of radiation signal presented to the
processor
[0107] H.sub.o is the electronic offset
[0108] Hc is corrected H (deg K..sup.4)
[0109] Tc is ambient and cold junction temperature (deg F.)
[0110] Taf is 4th power of Tamb (deg K..sup.4)
[0111] Tt is target temperature (deg F.)
[0112] Tz is ambient temp during cal (deg F.)
[0113] Td is the displayed temperature
[0114] Rt is the thermistor signal
[0115] Kh is a radiation sensor gain cal factor
[0116] Zt is a thermistor zero cal factor
[0117] Th is the hot junction temperature
[0118] .alpha..sub.ts is the Seebeck coefficient of the thermopile
at a specified temperature
[0119] J is the number of junctions in the thermopile
[0120] Tco is a temperature coefficient for the Seebeck
coefficient
[0121] Ts is the temperature at which .alpha..sub.ts is
specified
[0122] Tcr is core temperature
[0123] kc is a constant for computing core temperature
[0124] V.sub.s is the sensor output voltage
[0125] G.sub.FE is the gain of the front end amplifier
[0126] K.sub.AD is the analog-to-digital conversion factor
[0127] V.sub.s=(H-H.sub.0).sup.KAD/GFE
[0128] Tc(deg F.)=Thermistor lookup table (Rt)-Zt
[0129]
T.sub.H=[(Tco*T.sub.s+1).+-.[(Tco*Ts+1).sup.2-(2*Tco)*[(Tco((Tc*Ts)-
-(TC.sup.2/2))+Tc+(V.sub.s/J*.alpha..sub.ts)]].sup.1/2]/Tco
[0130] Hc(deg K..sup.4)=Kh*(H-H.sub.o)*(1+Tco*((Th-Tc)/2-Tz))
[0131] Thf(deg K..sup.4)=4th power lookup table (Tc)
[0132] Tt(deg F.)=(Hc+Thf).sup.1/4(Final lookup table)
[0133] Tcr=Te+(Tt-Te)/kc
[0134] Tt(deg C.)=(5/9)*(Tf(deg F.)-32) optional
[0135] The following is a list of the information which may be
contained in the EEPROM and therefore be programmable at the time
of calibration:
[0136] Radiation sensor offset
[0137] Radiation sensor gain
[0138] Radiation sensor temperature coefficient
[0139] Thermistor offset
[0140] Ambient temperature at calibration
[0141] Thermistor lookup table
[0142] Final temperature lookup table
[0143] Adjustment factor F
[0144] Sound source functions:
[0145] Beep at button push in lock mode
[0146] none/20/40/80 milliseconds long
[0147] Beep at lock
[0148] none/20/40/80 milliseconds long
[0149] Beep at power down
[0150] none/20/40/80 milliseconds long
[0151] Beep at lowbattery
[0152] none/20/40/80 milliseconds long
[0153] interval 1/2/3 sec
[0154] single/double beep
[0155] Timeout functions:
[0156] Time to power-down
[0157] 0.5 to 128 sec in 0.5 sec increments
[0158] Delay until lock
[0159] 0.5 to 128 sec in 0.5 sec increments
[0160] Other functions:
[0161] Power-on button resets lock cycle
[0162] Power-on button resets peak detect
[0163] Display degrees C./degrees F.
[0164] EEPROM "Calibrated" pattern to indicate that the device has
been calibrated
[0165] EEPROM checksum for a self-check by the processor
[0166] FIGS. 9A-9D provide a flowchart of the firmware stored in
the microprocessor 73. From reset when the instrument is turned on,
the system is initialized at 110 and the contents of the EEPROM are
read into memory in the microprocessor at 112. At 114, the
processor reads the state of power and mode switches in the system.
At 116, the system determines whether a mode switch 113 has placed
the system in a self-test mode. If not, all eights are displayed on
the four-digit display 82 for a brief time. At 120 , the system
performs all A-to-D conversions to obtain digital representations
of the thermopile output and the potentiometer settings through
multiplexor 76.
[0167] The system then enters a loop in which outputs dictated by
the mode switch are maintained. First the timers are updated at 122
and the switches are again read at 124. When the power is switched
off, from 126 the system enters a power down loop at 128 until the
system is fully down. At 130, the mode switch is checked and if
changed the system is reset. Although not in the tympanic
temperature detector, some detectors have a mode switch available
to the user so that the mode of operation can be changed within a
loop.
[0168] At 132, 136 and 140, the system determines its mode of
operation and enters the appropriate scan process 134, lock process
138 or peak process 142. In a scan process, the system updates the
output to the current reading in each loop. In a lock process, the
system updates the output but locks onto an output after some
period of time. In the peak process, the system output is the
highest indication noted during a scan. In each of these processes,
the system may respond to the programming from the EEPROM to
perform any number of functions as discussed above. In the peak
process which is selected for the tympanic temperature measurement,
the system locks onto a peak measurement after a preset period of
time. During assembly, the system may be set at a test mode 144
which will be described with respect to FIG. 9D.
[0169] In any of the above-mentioned modes, an output is calculated
at 146. Then the system loops back to step 122. The calculation 146
is illustrated in FIG. 9B.
[0170] At 148 in FIG. 9B, the raw sensor data is obtained from
memory. The sensor offset taken from the EEPROM is subtracted at
150, and the ambient temperature previously obtained from the
potentiometer RT1 is accessed at 152. The temperature coefficient
adjustment is calculated at 154. At 156, the sensed signal is
multiplied by the gain from EEPROM and by the temperature
coefficient. At 158, the fourth power of the ambient temperature is
obtained, and at 160 it is added to the sensor signal. At 162, the
fourth root of the sum is obtained through a lookup table. Whether
the display is in degrees centigrade or degrees Fahrenheit is
determined at 164. If in degrees centigrade, a conversion is
performed at 166. At 168, adjustment values, including that from
the potentiometer R4, are added.
[0171] Analog-to-Digital conversion is performed periodically
during an interrupt to the loop of FIG. 9A which occurs every two
milliseconds. The interrupt routine is illustrated in FIG. 9C.
Timer counters are updated at 170. A-to-D conversions are made from
172 only every 100 milliseconds when a flag has been set in the
prior interrupt cycle. During most interrupts, an A/D conversion
does not occur. Then, the 100-millisecond counter is checked at
174, and if the count has expired, a flag is set at 176 for the
next interrupt. The flag is checked at 178 and, if found, the
display is updated at 180. The system then returns to the main loop
of FIG. 9A.
[0172] Where the 100 millisecond flag is noted at 172, an A-to-D
conversion is to be performed. The system first determines at 182
whether a count indicates there should be a conversion of the
thermopile output at 184 or a conversion of the thermistor output
at 186. The thermopile sensor conversion is performed nine out of
ten cycles through the conversion loop. At 188, the system checks
to determine whether a conversion is made from the potentiometer R4
or from the battery voltage divider R1, R2 at 192. These
conversions are made alternately.
[0173] FIG. 9D illustrates the self-test sequence which is called
by the mode switch 113 only during assembly. During the test, the
beeper sounds at 182 and all display segments are displayed at 184.
Then the system steps each character of the display from zero
through nine at 186. The system then enters a test loop. At 188,
the system senses whether the button 108 has been pressed. If so, a
display counter is incremented at 190. The display for the unit
then depends on the count of the display counter. With the zero
count, the adjustment potentiometer value is displayed at 192.
Thereafter, if the display counter is incremented by pressing the
button 108, the raw sensor data is displayed. With the next
increment, ambient temperature is displayed at 196, and with the
next increment, the raw output from the ambient temperature sensor
RT1 is displayed. With the next increment, the battery voltage is
displayed. After the test, the assembler sets the mode switch to
the proper operating mode.
[0174] While this invention has been particularly shown and
described with references to preferred embodiments thereof, it will
be understood by those skilled in the art that various changes in
form and details may be made therein without departing from the
spirit and scope of the invention as defined by the appended
claims. For example, most features of the invention may be applied
to a device having a pyroelectric radiation sensor. Also certain
features such as the low reflectance, high thermal conductivity
tube may provide stable response and narrow field of view even
where the tube is thermally isolated from the sensor. In that case,
a second temperature sensor would be provided for the tube to
compensate for temperature differences between the tube and sensor
cold junction.
* * * * *