ANALYZING SYSTEM WITH DISPOSABLE CALIBRATION DEVICE
BACKGROUND OF THE INVENTION
1. Field of the Invention
This invention relates to instruments that measure characteristics and/or
conditions of target materials or tissues, and in particular, to such instruments that
utilize a calibration device. The invention also relates to apparatus and methods of
determining a patient bilirubin concentration.
2. Background of the Related Art
There are a variety of measuring instruments that utilize light to detect
physical characteristics or conditions of a material. Some such instruments are used
by medical personnel to determine a condition of a patient. The use of light to
determine a characteristic or condition of a target material is generally called
spectroscopy. Spectroscopy has become more common in medical applications with
the development of appropriate and inexpensive light sources, detection devices and
optical fibers that allow for minimal invasiveness.
Typically, spectral reflectance, scattering, transmittance, fluorescence (normal
and time resolved) and Raman spectroscopy are used to evaluate materials in order
to determine the types of materials present and to measure their concentrations.
One type of spectroscopy, reflectance spectroscopy, involves diffusely
reflecting light from a target material, and analyzing the reflected light. In another
type of spectroscopy, called transmittance spectroscopy, light passes through a target
material, and the transmitted light is analyzed. In other spectroscopic methods,
illuminating a target material may cause the target material to emit fluorescent or
luminescent light that can then be analyzed. In still other spectroscopic methods, a
target material may be illuminated with polarized light, and reflected or transmitted
light is analyzed to determine how the polarization of the light has changed. The
polarization change can be used to determine characteristics or conditions of the
target material.
An example of a spectroscopic measuring instrument is shown in Figure 3C.
The instrument 3 emits light, at one or more wavelengths, from a nose portion.
Light that is scattered or reflected from a target material 40, or light generated by the
target material, is then collected and analyzed by the instrument to determine a
characteristic or condition of the target material 40.
Spectroscopic instrument accuracy can be affected by variations in light source
intensity, spectral characteristics, lens-aging, lens cleanliness, temperature, detector
sensitivity changes, and electronic drifting. To correct for any potential measuring
inaccuracies, it is common to periodically calibrate a spectroscopic measuring
instrument. Calibration techniques usually involve conducting a measurement on
a test target having characteristics that remain stable over time and over a range of
temperatures. The calibration techniques can be used to compensate for instrument
to instrument variations, and for any changes that an individual instrument may
experience over its working lifetime.
During a calibration operation, a spectroscopic measuring instrument is aimed
at a calibration target having known optical properties. Light is then scattered or
reflected by the calibration target, and received back in the instrument. Because the
calibration target has known optical properties, the instrument is able to perform a
calibration operation to ensure that the instrument continues to deliver accurate
results.
Also, some measuring instruments may use a reference target as part of a
measurement process. In such a device, the instrument is aimed at a reference target
having known optical properties. Light from the instrument is scattered or reflected
from the reference target, and a reading is taken. The results of the measurement
operation conducted on the reference target can then be used as a standard or
reference against which patient measurements are judged. For instance, the result of
a patient reading could be derived by determining a difference or ratio between a
patient reading and a reading taken on a reference target. Because the optical
properties of the reference target are known, variations in light output or detector
sensitivity can be accounted for by use of the reference target.
Throughout the remainder of the application, including the claims, the terms
"calibration target" and "reference target" are used interchangeably. Any reference
to a calibration target is equally applicable to a reference target, and vice versa.
When a measuring instrument is used with human or animal patients, steps
must be taken to ensure that use of the instrument does not contaminate or infect the
patient. When the instrument is successively used to examine two different patients,
steps must be taken to ensure that there is no cross contamination between the
patients.
Although others have proposed calibration fixtures that compensate for the
above-described variations in instrument performance, none have provided a
simultaneous solution to both the calibration issue and the problems associated with
the spread of infection in a medical setting. Furthermore, calibration devices that are
designed to be re-used can become damaged by sunlight, temperature, humidity and
other effects, which could lead to errors in calibration.
One application of spectroscopic measurement systems involves detection of
a bilirubin concentration in a human. Bilirubin is produced from the breakdown of
hemoglobin in red blood cells. Under normal conditions, the bilirubin is conjugated
by glucoronyl transferase, an enzyme present in the liver, and is then excreted
through the biliary system.
Newborn infants and prematurely born infants are particularly susceptible to
hyperbihrubinemia. Hyperbihrubinemia describes the state where there is excessive
bilirubin in the body. Often this is due to the lack of functioning glucoronyl
transferase enzyme in their liver, or excessive red blood cell breakdown associated
with erythroblastosis fetalis.
One method for bilirubin testing includes blood based lab assay testing. The
"heel stick" blood lab assay is currently the only accepted methodology for
quantitative bilirubin testing results in the United States. Of course, this invasive
approach requires that blood be drawn to perform the test.
Non-invasive measurements of the bilirubin concentration would eliminate
the need to draw blood samples from patients for bilirubin analysis. It would also
provide easy patient interface. It is known that bilirubin can be measured non-
invasively by taking reflectance measurements from a patient's skin, from the
aqueous of the eye, or from the sclera (white) of the eye, based on the fluorescent
signature. Reflectance measurements can also be made on the tympanic membrane
of the ear. This is possible because bilirubin from the blood stains the skin as well
as other tissues of the body. Jaundice refers to the condition when the bilirubin is
visible in the skin and sclera.
Many attempts have been made to measure cutaneous bilirubin non-invasively.
These attempts include the development of visual reference standards, and
transcutaneous reflectance spectroscopy to measure the absorption spectra of
bilirubin, oxidized blood, and melanin, the dominant absorbers in the skin. The
concentration of these pigments have distinct absorption spectra.
Reflectance bilirubinometers have obtained reasonable correlations between
bilirubin levels determined transcutaneously and serum bilirubin concentrations in
homogeneous patient populations. Unfortunately, these devices have failed to give
satisfactory correlations when used over a heterogeneous population. Since patient
populations are rarely homogeneous, transcutaneous bilirubin measuring methods
have not been widely accepted clinically.
SUMMARY OF THE INVENTION
An object of the invention is to provide a measurement system with a
disposable calibration device that is inexpensive and that helps to prevent
contamination or infection.
Another object of the invention is to provide a spectroscopic system which
uses a calibration device which provides an optically clear, scratch-free window
between the optical instrument and the tissue or material to be measured.
It is also an object of the invention to provide a disposable calibration target
configured for single use only.
Another object of the invention is to provide a simple and accurate apparatus
and method of measuring a patient's bilirubin concentration.
A further object of the invention is to provide a system and method for
comparing the optical characteristics of a first target material to optical characteristics
of a second target material.
A measuring instrument embodying the invention transmits radiation to a
material or tissue and receives and analyzes radiation transmitted through, reflected
from or scattered from, or generated by the material or tissue being measured. In
some embodiments, the radiation emitted by the instrument may be polarized, and
the polarization orientation of the transmitted, reflected/scattered or generated
radiation may be analyzed by the instrument. Also, particular embodiments of the
invention may combine multiple ones of the above listed techniques to arrive at a
diagnosis of a patient, or to provide an analysis of a target material.
A measuring instrument embodying the invention may include a spectrometer
capable of determining the amplitude of radiation at any of a plurality of
wavelengths. Alternatively, the measuring instrument may comprise a detector and
one or more filters for selectively focusing radiation of specified wavelengths upon
the detector. The measuring instrument could also comprise a plurality of filters and
a corresponding plurality of detectors, where radiation from a target material passes
through the filters and onto the detectors so that each detector receives radiation at
a different wavelength. The measuring instrument might also comprise a diffraction
grating and a plurality of detectors, wherein the diffraction grating focuses radiation
of predetermined wavelengths on respective ones of the plurality of detectors. Still
further, the radiation analyzer may comprise a radiation detector and a linear variable
filter.
In still other embodiments of the invention, a measuring system could include
a plurality of emitter and detector pairs arranged in an array on the measuring
instrument. Light output from the emitters could reflect/scatter/transmit from a
target material or tissue or light could be emitted from the material or tissue, and the
light would be received by the corresponding detectors. In another embodiment,
the measuring system could include a single light source for illuminating a target
material or tissue, and an array of detectors, such as a charge coupled device (CCD),
for receiving light that is reflected/scattered/transmitted/emitted from the target
material or tissue. Each of these embodiments would allow the measuring
instrument to develop an image of the target material or tissue, or an image of
reflective/transmissive/fluorescent properties of the target material or tissue.
A measurement instrument embodying the invention also may include one or
more transmit and receive fiber optic waveguides for directing electromagnetic
radiation to a material or tissue to be measured and for conducting radiation from a
target material or tissue back to a sensor of the instrument. The instrument may be
configured such that radiation transmitted from the instrument toward the material
or tissue being measured is directed toward the material or tissue at an angle relative
to a plane normal to the surface of the material or tissue so as to reduce
backscattering effects.
A method and device embodying the invention may measure a bilirubin
concentration in a patient using the amplitude of radiation reflected from a patient's
skin at first and second wavelengths representing a blood content of the skin, and at
a third wavelength representing an uncorrected bilirubin concentration. Such a
method and instrument may also utilize the amplitude of reflected radiation at fourth
and fifth wavelengths that represent a melanin content of the patient's skin.
A measuring instrument embodying the invention may include a calibration
device that includes a structure through which radiation can be transmitted. The
calibration device may also include a removable calibration target arranged on said
structure and capable of returning a portion of radiation output by the instrument
back to a sensor of the instrument for purposes of conducting a calibration operation.
In alternate embodiments, radiation may be transmitted through the calibration
target before passing to a sensor of the instrument. In still other embodiments, the
calibration target may include a fluorescent or luminescent portion that emits
fluorescent or luminescent radiation towards a sensor of the measuring instrument
for purposes of conducting a calibration operation. The removable calibration target
is configured to be removed from the structure of the calibration device after a
calibration operation is completed, while the structure remains attached to the
measuring instrument, so that radiation can pass through the structure during a
subsequent measuring operation.
When the instrument is for medical diagnostic purposes, a calibration device
embodying the invention may include a shield to prevent patient contamination or
infection. In some embodiments, the calibration device may comprise both an
infection shield and a calibration or reference target with known optical properties
integrated into a single unitary element.
In preferred embodiments, the removable calibration target is configured such
that a portion of the calibration target having predetermined optical characteristics
is destructively altered when it is removed from a structure of the calibration device.
As will be explained more fully below, configuring the calibration device so that it
can only be used once can help to prevent patient infection or cross-contamination.
A calibration device embodying the invention may also include an index
matching substance, such as a gel, that can be interposed between a material or tissue
being measured and a distal end of a measurement instrument.
In one method embodying the invention, a reference target is attached to an
output end of a measuring instrument. A first measurement is then taken with a
light source of the measurement instrument turned off. This is called a dark
reference reading. Next, a measurement is taken on the reference target with the
ght source turned on. This is termed a reference reading. The reference target is
then removed from the measurement instrument, and a first measurement is
conducted on a patient or an object with the light source of the instrument turned
off. This is termed a dark object reading. Next, a patient or object measurement is
conducted with the light source turned on. This is termed an object reading. A ratio
is then created with a difference between the object reading and the dark object
reading in the numerator, and a difference between the reference reading and the dark
reference reading being in the denominator. By creating a ratio of the differences,
any variation in the light output of the measurement instrument or of the detector
sensitivity cancels out to provide an accurate measurement result.
In addition, the reference reading, dark reference reading, skin reading and
dark skin reading can all be corrected for "stray light." The correction for stray light
also helps to ensure that the measurement reading is more accurate. A method and
formula for calculating and correcting for stray light is provided in the detailed
description below.
Additional advantages, objects, and features of the invention will be set forth
in part in the description which follows, and in part will become apparent to those
having ordinary skill in the art upon examination of the following, or may be learned
from practice of the invention. The objects and advantages of the invention may be
realized and attained as particularly pointed out in the appended claims.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1A shows a schematic view of a measurement system in a calibration
mode;
Figure IB shows a measurement system in a measurement mode wherein a
calibration target has been removed and radiation is reaching a tissue or material to
be measured;
Figure 2A shows a schematic representation of a calibration device embodying
the invention;
Figure 2B shows the calibration device of Figure 2A after a calibration target
is removed from a window of the device;
Figure 2C shows a schematic sectional representation of another calibration
device embodying the invention;
Figure 2D is a schematic representation of the calibration device of Figure 2C
after a removable seal has been removed;
Figure 2E shows a schematic representation of the calibration device of Figure
2C mounted on a measurement instrument after a calibration target has been
removed from the device;
Figure 2F is a schematic sectional representation of a calibration device
embodying the invention;
Figure 2G shows the calibration device of Figure 2F mounted on a
measurement instrument after a removable calibration target has been removed from
the device;
Figure 3A is a schematic representation of another calibration device
embodying the invention;
Figure 3B is a schematic representation of the calibration device of Figure 3 A,
positioned adjacent a material or tissue to be measured, with a calibration target
partially removed from the device;
Figure 3C shows a measurement system embodying the invention which
utilizes a disposable calibration device as shown in Figures 3A and 3B;
Figure 3D shows the measurement system of Figure 3C with the calibration
device removed;
Figure 3E is a cross-sectional view of a measurement system embodying the
invention that includes a spring loaded annulus at a distal end of the measurement
instrument;
Figure 3F is a flow chart summarizing the steps involved in calibrating a
measurement instrument and taking a measurement on a material or tissue using a
method embodying the invention;
Figure 4 is a perspective view of a structure of a calibration device embodying
the invention;
Figure 5A is a side view of a calibration device embodying the invention;
Figure 5B is a sectional view of another calibration device embodying the
invention;
Figure 6 is a schematic representation of another calibration device embodying
the invention.
Figure 7A is a schematic side view of another calibration device embodying
the invention;
Figure 7B is a front view of the calibration device of Figure 7A;
Figure 8 is an exploded perspective view of a calibration target embodying the
invention that could be used in a measuring system embodying the invention;
Figure 9 is an exploded perspective view of a combined calibration/reference
target and infection shield embodying the invention that could be used in a
measuring system embodying the invention;
Figure 10 is a plan view of another calibration/reference target embodying the
invention that could be used in a measuring system embodying the invention;
Figure 11 is another plan view of a calibration/reference target embodying the
invention that could be used in a measuring system embodying the invention;
Figure 12 is a plan view of another calibration/reference target embodying the
invention that could be used in a measuring system embodying the invention;
Figure 13 is a sectional side view of a calibration device embodying the
invention;
Figure 14 is an exploded perspective view of a calibration/reference target and
infection shield that could be used in a measuring system embodying the invention;
Figure 15 A is a side sectional view of a calibration device embodying the
invention;
Figure 15B is a perspective view of the calibration device of Figure 15 A;
Figure 16 is a plan view of another calibration/reference target embodying the
invention that could be used in a measuring system embodying the invention;
Figure 17 is a side view of another calibration/reference device embodying the
invention that could be used in a measuring system embodying the invention;
Figure 18 is a perspective view of another calibration/reference device
embodying the invention that could be used in a measuring system embodying the
invention;
Figure 19 is a plan view of another calibration/reference target embodying the
invention that could be used in a measuring system embodying the invention;
Figure 20 is a plan view of another calibration/reference target embodying the
invention that could be used in a measuring system embodying the invention;
Figure 21 is yet another embodiment of a calibration/reference target
embodying the invention that could be used in a measuring system embodying the
invention;
Figure 22 is a diagram of an external light source that can be used with a
measuring instrument and transmissive calibration/reference device embodying the
invention;
Figure 23 is a diagram showing a measuring instrument embodying the
invention performing a calibration operation or a measurement operation utilizing
an external light source;
Figure 24A is a diagram of a measuring instrument embodying the invention;
Figure 24B is a diagram showing a measuring instrument embodying the
invention conducting a calibration/reference operation with a transmissive
calibration target;
Figures 25A, 25B, and 25C show front, side and back views, respectively, of
a measurement instrument embodying the invention;
Figure 25D shows a measurement instrument embodying the invention in a
charging stand;
Figure 26A is a schematic diagram of certain elements of a measuring
instrument embodying the invention;
Figure 26B shows a cut away perspective view of an optical unit of the
measurement instrument of Figure 26A;
Figure 27 is a diagram showing a fiber optic bundle of a measurement
instrument embodying the invention adjacent a tissue or material being measured;
Figure 28 is a sectional view of the fiber optic bundle of Figure 27 as seen from
section line 28-28;
Figure 29 is a sectional view of the fiber optic bundle of Figure 27 as seen from
section line 29-29;
Figure 30 is a diagram showing transmit and receiving optical fibers of a
measurement instrument embodying the invention and the path of radiation emitted
or received by the optical fibers;
Figure 31 is a block diagram of parts of a measurement instrument embodying
the invention;
Figure 32 is a flow chart showing the steps of a method embodying the
invention for calculating a bilirubin concentration of a patient;
Figure 33 is a diagram showing the results of data taken using the method of
Figure 24 versus a standard serum bilirubin (heel stick) method;
Figure 34 is a flow chart of another method embodying the invention for
calculating a bilirubin concentration of a patient;
Figure 35 is a diagram showing the amplitude of light reflected from a patient's
skin under two conditions, the first condition corresponding to blood in the patient's
skin being 100% oxygenated and the second condition corresponding to the blood
in the patient's skin having no oxygen;
Figure 36 is a diagram showing the amplitude of radiation reflected or
scattered from a patient's skin for explaining how a corrected bilirubin concentration
is calculated using a method embodying the invention;
Figure 37 is a flowchart of a method of performing bilirubin measurements on
a patient embodying the invention;
DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS
The terms "calibration target" and "reference target" are used interchangeably
in the following text to refer to a target having known optical properties. The
invention is applicable to both calibration targets and reference targets, and use of
either term should not be construed as limiting. Also measuring instruments
embodying the invention make use of electromagnetic radiation. The terms
electromagnetic radiation, radiation and light are intended to be equivalent terms, all
of which refer to electromagnetic radiation.
Figure 1A is a schematic view of a spectroscopic measurement system 3 in a
calibration mode. The system 3 includes an instrument 10 which outputs
electromagnetic radiation 39 and receives and analyzes radiation reflected back
towards the device by a material or tissue 30 being measured, or that is generated by
the material or tissue 30 in response to the radiation output by the instrument 10.
Alternatively, the instrument 10 may output, receive and analyze acoustic waves.
Reference number 39 will be used to represent electromagnetic radiation or acoustic
waves, just as reference number 10 will be used to represent an instrument that
outputs either electromagnetic radiation or acoustic waves.
The electromagnetic radiation 39 output by the instrument 10, or that is
generated by a material or tissue or a calibration target, may lie within the visible,
infrared, ultra-violet regimes, and/or within the rf, microwave and millimeter wave
regimes. With regard to electromagnetic radiation 39, the instrument 10 can be a
spectrometer, laser radar, radar or any other radiation measuring instrument that
outputs radiation to a material or tissue 40, then measures some portion of a return
signal.
With regard to acoustic waves, the instrument 10 can be an acoustic
measuring/imaging device that outputs acoustic waves and measures the return
acoustic wave signal. The discussion that follows is drawn to a device that uses
electromagnetic radiation, it being understood that an analogous discussion applies
for an instrument that uses acoustic waves.
During a calibration procedure, as shown in Figure 1A, radiation 39 is
transmitted toward and through a shield 20 toward a calibration target 30. The shield
20 serves as a barrier between the instrument 10 and a material or tissue 40 to be
measured, and hence functions to reduce contamination of the material or tissue 40.
One major (but not the only) purpose of the shield 20 is to guard against possible
infection when living tissue 40 is measured. Hence, the shield 20 might also be
referred to as an infection shield. A shield 20 must be at least partially transmissive
to radiation 39 such that a portion of the emitted radiation passes through the
window 20 to appear as radiation 39'.
Radiation 39' passes through a region 35 and reaches a surface 41 of the
calibration target 30. The surface 41 can be the same material as the calibration target
30, or a specially applied layer. The surface 41 reflects or scatters radiation back
towards the instrument 10, or emits flourescent or luminescent radiation. Note that
throughout this specification, reflection and scattering are used interchangeably and
are meant to indicate that radiation travels back toward instrument 10. Also, the
region 35 can include a variety of adhesives, gels, pastes, or other materials.
Once the system 3 with the instrument 10 is calibrated, the calibration target
30 is removed, and the system 3 is ready to take measurements on a target material
40 through the shield 20. Figure IB shows the system 3 in a measurement mode,
wherein the calibration target 30 has been removed and radiation 39' is now reaching
a tissue or material 40 to be measured through the shield 20.
Figure 2A shows a schematic representation of a calibration device 45
embodying the invention. The calibration device 45 includes a shield supporting
structure 250 with a window 260. Together, the structure 250 and the window 260
comprise the shield 20 shown in Figure 1 A. In alternative embodiments, the window
260 can be an opening in the structure 250, or a transmissive barrier. Any reference
to a window should be read to encompass either an opening or a transmissive
structure, where appropriate. Also, in this embodiment, the supporting structure 250
is shaped like a truncated cone. As a result, the window 260 is circular. It should be
understood, however, that the shape of the shield structure 250 need not be limited
to a cone-type shape, and the window 260 need not be limited to a circular shape.
The calibration device 45 also includes a calibration target 270 (corresponding to the
calibration target 30 in Figure 1A) with a user graspable tab 280. The calibration
target 270 is arranged in the window 260 of the structure 250.
The calibration device 45 receives radiation 39 from an instrument 10. The
radiation 39 passes through the window 260 and the region 35 and reaches the surface
41 of the calibration target 270. The window 260 must be at least partially (and
preferably nearly completely) transparent to the radiation 39. The region 35 can
include an adhesive, gel, or liquid which may act as an index matching agent, and/or
free space. In one embodiment, the window 260 is statically charged with respect to
surface 41 of calibration target 270. The static charge holds the calibration target 270
in place. Radiation 39 is then incident on the surface 41 of the calibration target 270.
If the calibration target 270 is to be reflective, it should be configured to have
a known reflection spectrum for calibration purposes (note that the radiation 39 is
scattered or reflected from the calibration target 270 back towards the instrument 10).
For instruments 10 which perform measurements of intensity, independent of
wavelength, a highly reflective surface 41 of the calibration target 270 may be
advantageous. This might include radar, laser radar and interferometric type
instruments. Note, however, that such instruments might also benefit from using a
less reflective surface 41 on the calibration target 270.
Once a measurement system is calibrated, the calibration target 270 is removed
from the window 260 by pulling on a user graspable tab 280, as shown in Figure 2B.
The system 3 is now ready to take measurements on a material or tissue 40 through
the window 260 of the calibration device.
Figures 2C through 2E show an embodiment of the calibration device that
includes an index matching agent. As shown in these figures, the calibration device
includes a structure 250, a calibration target 270 having a calibration surface 41 and
an index matching agent 293 contained within the structure 250 and covered with a
seal 290. The index matching agent 293 could be a liquid or a gel that aids the
instrument in taking an accurate measurement.
To use a calibration device that includes an index matching agent, one would
first remove the seal 290 using a user graspable tab 295. The calibration device,
without the seal 290, is shown in Figure 2D. The calibration device would then be
attached to a housing 298 of a measurement instrument, as shown in Figure 2E. The
housing may include a window 294 designed to abut the index matching agent 293
when the structure of the calibration device is mounted on the instrument. A bundle
of optical fibers 299, that transmit and receive radiation, may abut the other side of
the window 294.
Once the structure 250 of the calibration device is mounted on the housing
298 of the measurement instrument, a calibration measurement would be performed
while the calibration target 270 is still attached to the structure 250. After the
measurement instrument has been calibrated, the calibration target 270 would be
removed from the structure 250 so that measurements can be performed on a
material or tissue. All or a portion of the structure 250 may be made of a flexible
material so that the structure 250 can flex when the instrument is pressed against a
target material, or the skin of a patient. This would cause the index matching agent
293 to completely fill the void between the target material/patient's skin and the
window 294 of the measurement instrument.
Another calibration device embodying the invention is shown in Figures 2F
and 2G. In this embodiment, the calibration device includes a structure 250 and a
window 297. A calibration target 270 is attached to the structure 250 and an index
matching agent 293 is trapped between the window 297 and the calibration target
270.
The calibration target would be mounted on a housing 298 of a measuring
instrument, as shown in Figure 2G. A bundle of optical fibers 299 can then abut a
first side of the window 297 opposite the index matching agent 293. Once the
calibration device is attached to the measurement instrument, a calibration
measurement can be performed while the calibration target 270 is still attached to the
structure 250. After calibration has occurred, the calibration target 270 could be
removed so that measurements can be performed on a material or tissue.
Figures 3A and 3B correspond to Figures 2A and 2B, but with radiation 39
entering from the right side, and the calibration target 270 attached to the window
260 within the structure 250. In this case, an outer annular ring 306 comes into
contact with a tissue or material 40 to be measured. Structure 250 also includes an
annular ring or ridge 312, which is intended to be used to secure the device 45 to an
instrument 10 (not shown).
Figure 3C shows a measurement system 3 which utilizes a disposable
calibration device 45. Here, the measurement instrument 10 is an optical instrument,
such as a spectrometer, and radiation 39 is electromagnetic radiation which can be in
the visible, UV and/or infrared regions. The system 3 includes a housing 343 which
is easily graspable by a human hand. The instrument 10 is coupled to calibration
device 45 via optical fibers 333. The calibration device 45 is inserted into an opening
end 346 of a cone-shaped holder 358 of the housing 343. The cone shaped holder 358
can have any shape depending, among other things, on the shape of the calibration
device. Hence, the holder 358 will alternatively be referred to as a calibration device
receiving element. The holder 358 can be a separate piece, or part of the housing 343.
It is preferable that the holder 358 be capable of receiving the calibration device 45
and allowing the calibration target to be readily removed from the calibration device
so that a measurement may be performed on a material or tissue 40. The holder 358
should also allow the calibration device 45 to be easily removed so that the system
3 is again ready to receive a new calibration device 45.
A curved portion 366 ofthe housing 343 allows the user's hand to comfortably
hold the system 3. A user can initiate a calibration or measurement, as the case may
be, by pressing a push button 361 with his or her thumb. Once a calibration
measurement has been performed, a user graspable tab 280 is used to remove the
calibration target from the window 260 (not shown in this view), and the system 3
is ready to make a measurement on a material or tissue 40.
Figure 3D shows the same measurement system with the calibration device 45
removed. A new calibration device 45 must be inserted into the holding end 346 of
the system 3, the above discussed process of calibration repeated, and the calibration
target 270 removed, before the measurement system 3 is ready to perform a new
measurement. Alternatively, a cap 375 can be placed over the holding end 346
between measurements. In all of the above embodiments, the calibration target 270
can have calibration information fitted directly on the surface 41 of the calibration
target 270. This calibration information can include a message read by the
instrument 10, or a particular pattern that can be recognized by the instrument. In
such a system, if a calibration target does not include the predetermined message or
pattern, the instrument could be configured to shut down. This would prevent the
use of unauthorized calibration targets, which would help to ensure the instrument
is always properly calibrated.
Figure 3E shows a cross-sectional view of a measurement instrument
embodying the invention. The instrument includes a measurement device 10 coupled
to an output end 370 of the system 3. An annulus 372, that surrounds a bundle of
optical fibers 333, is mounted on the output end 370 of the system 3. The annulus
372 is mounted on the system 3 utilizing a spring 373, which biases the annulus 372
outward away from the measurement system 3. The annulus 372 may also be
connected to a device that senses the position of the annulus 372 relative to the
housing of the system 3.
According to one embodiment of the invention, the measurement device
functions independently of spring 373 in that a measurement can be made regardless
of whether or not spring 373 is biased. According to another embodiment of the
invention, when a user performs a measurement using the measurement system 3, the
user would push the instrument against a surface of a target material, or the skin of
a patient, so that the annulus 372 moves inward, against the bias of the spring 373.
The movement would be sensed by a proximity sensing device. The proximity
sensing device could then be used to output a signal when the annulus 372 is pushed
far enough into the measurement system 3 such that a measurement can be
performed by the measurement system 3. In a measurement system including a
spring biased annulus 373, the proximity sensing device could be used to disable the
device when the annulus 373 is too far out, and to enable the device to take a
measurement when the annulus 372 is pushed a sufficient distance into the device
such that a measurement can be accurately performed. The proximity sensing device
could be a simple switch having electrical contacts, or a light emitter and
corresponding sensor. Alternatively, the proximity sensor could directly sense the
proximity of an output end of the measurement instrument to a target material or
tissue using an optical system or some other equivalent sensor, as would be well
known in the art.
Figure 3F summarizes the steps involved for the system 3 to take a
measurement on a material or tissue 40. In particular, step 382 involves placing a
calibration device 45 on the end 346 of the system 3. At this point, the calibration
45 device still has a calibration target 270 covering the window 260. A calibration
measurement is performed by the system 3 at step 384 by pressing a push button 361,
which activates the measurement instrument 10. Step 388 involves removing the
calibration target 270 from the window 260. Step 392 then involves performing a
measurement on a tissue or material 40 to be measured. This might involve a single
measurement or multiple measurements (if cross contamination is not an issue) on
the same or a similar tissue or material. That is, multiple measurements might be
taken in one vicinity, or at different locations on a material or tissue. The results of
the multiple measurements could be averaged or interpreted to arrive at a
measurement result. Finally, once the measurement or measurements have been
completed, the calibration device 45 is removed, discarded, and replaced with a new
calibration device 45 at step 396. Alternatively, a used calibration device 45 can be
removed, discarded, and a cap 375 can be placed over the end 346 until a new
measurement is to be made.
A calibration/reference device embodying the invention, that could be used
with a measuring system embodying the invention, may be comprised of several
parts. The first part is simply a device for anchoring a contamination/infection
shield and a calibration/reference target to a measuring instrument. If the instrument
is like the one shown in Figure 3C or 3E, a shield holder 110, as shown in Figure 4,
can be used to attach an infection/contamination shield and a calibration/reference
target to the nose portion of the measuring instrument.
As seen in Figures 4, 5 A and 5B, the shield holder 110 has a plurality of finger¬
like projections 114 arranged in a cylindrical shape. Some or all of the projections
114 may include a lip 116 which is engageable with the nose portion of the
instrument to attach the device to the instrument. The projections might also engage
a spring loaded mechanism like the one shown in Figure 3E. If the shield holder 110
is made from a flexible material, such as a molded plastic, the shield holder 110 can
be snapped onto the nose of the instrument so that the lips 116 engage the nose.
A multilayer combined contamination shield and calibration target 200 can
then be affixed to a front annular surface 112 of the shield holder 110, as shown in
Figure 5A. In a preferred embodiment of the invention, the combined
contamination shield and calibration target 200 is attached to the shield holder 110
with a layer of adhesive. The combined contamination shield and calibration target
200 may include a user graspable tab 202 for removing the calibration target after a
calibration or reference operation has been performed.
Of course a calibration target 200 could also be mechanically attached to the
shield holder 110 by any type of mechanical attachment mechanism such as staples,
clips, pins, etc. Figure 17, which is described in more detail below, shows an
embodiment where a calibration target 206 is attached to a shield holder 110 with a
plurality of pins 220 arranged around the periphery of the shield holder 110.
In an alternate embodiment, as shown in Figure 5B, an infection shield 204
may be separately mounted to the shield holder 110. The infection shield 204 could
simply be a clear plastic portion of the shield holder 110, which is integrally molded
with the shield holder 110. The infection shield 204 could also be a substantially
transparent film that is attached to the shield holder 110. A calibration target 206
could then be attached to the front annular surface 112 of the shield holder 110 via
an adhesive layer or some type of mechanical attachment device. The calibration
target 206 would include a user graspable tab 202 for aiding removal of the calibration
target after a calibration or reference operation has been performed.
Figure 6 shows a calibration device 45 according to another embodiment of
the invention. Here, a landing annulus 690 is affixed to the structure 250. The
landing annulus 690 serves to fix the angle at which radiation is incident on the
surface 680 of a material or tissue 40 being measured. The landing annulus 690 is
preferably transparent to radiation 39. Calibration occurs, as before, using the
calibration target 270. The calibration target 270 is then removed, and the annulus
690 remains in place. The measuring instrument, is then placed on the surface 680,
such that the annulus 690 lies flat on the surface 680. This ensures that radiation 39
is incident approximately normal to the surface 680, as it was to the surface 41 of the
calibration target 270. On the other hand, depending on the type of measurement,
it may be preferable, due to unwanted spectral reflections, to have radiation 39
incident at an angle relative to an axis normal to the surface 680. The landing
annulus 690 can be a separate piece affixed to the structure 250 and comprised of any
type of rigid material such as various plastics. If infection to the surface 680 of tissue
40 is an issue, then the landing annulus 690 should be removable from the structure
250. Alternatively, annulus 690 can simply be an extension of window 260 itself.
The structure 250 is preferably fabricated from molded plastic with a smooth
window zone defined for the window 260. Using plastic molding allows the
structure 250 to be fabricated at low cost and in a wide variety of shapes and sizes.
The calibration target 270 can also be fabricated from plastic and may also have a dye
or other material added to the surface 41 to provide sufficient spectral detail to effect
the necessary calibration. The calibration target 270 can be attached to the window
section 260 in such a way that once removed, it cannot be readily re-attached. One
implementation is to fabricate the calibration target 270 using a statically clinging
type plastic, and to fabricate structure 250 using an appropriate material such as an
acrylic called polymethyl methacrylate (PMMA), both of which are available from
3M Corporation.
Figure 7A shows a side view of a calibration device 45 according to yet another
embodiment of the invention. Here, the calibration target 270 is held in place by a
ridge 700 alone, or together with static cling between the calibration target 270 and
the window 260. The ridge 700 can be part of the window 260, or a separate piece.
Figure 7B shows the calibration device 45 as viewed from above.
A calibration/reference target that could be used with a calibration target
embodying the invention is shown in Figure 8. The target includes a calibration
layer 470 having a central portion 474 with known optical properties. A user
graspable tab 472 is formed as a part of the calibration layer 470. Also, a double-sided
adhesive layer 440 is used to attach the calibration layer 470 to a shield holder 110,
as shown in Figure 5B. In alternate embodiments, the adhesive layer 440 can be used
to attach the calibration layer 470 to an infection/contamination shield layer which
is then attached to the shield holder 110, as shown in Figure 5 A. Also, the adhesive
layer 440 could be used to attach the calibration layer 470 directly to a measuring
instrument. In still other embodiments, the double-sided adhesive layer 440 could
be replaced with an adhesive that is applied to the calibration layer 470 in a liquid,
gel or paste form.
In preferred embodiments, the calibration layer 470 and the double-sided
adhesive layer 440 are carefully constructed so that when the calibration target is
removed from a shield holder, the target portion 474 in the center of the calibration
layer 470 will tear in a predetermined manner. To that end, the calibration layer 470
may include a reduced strength portion 480, which could be a slit, a perforation or
a crease. The reduced strength portion 480 in the embodiment shown in Figure 8 is
a perforation that extends from a peripheral edge of the calibration layer 470, towards
the central area 474. When a user grasps the tab 472 and pulls on the tab to remove
the calibration layer 470 from a shield holder, the calibration layer 470 will tend to
tear along the reduced strength portion 480.
In the embodiment shown in Figure 8, the adhesive layer 440 has a horseshoe
shape such that a portion of the calibration layer 470 having the reduced strength
portion 480 is aligned with the gap in the adhesive layer 440. Also, in a preferred
embodiment, a first side 442 of the adhesive layer 440 will have a relatively low
adhesive strength, and the opposite side of the adhesive layer 440 will have a greater
adhesive strength. In this configuration, the lower adhesive strength side 442 of the
adhesive layer 440 is used to attach the calibration layer 470 to a shield holder. When
a user pulls on the tab 472 to remove the calibration layer 470, the lower adhesive
strength side 442 will separate from the shield holder before the higher adhesive
strength side separates from the calibration layer 470. Thus, the adhesive layer 440
is fully removed along with the calibration layer 470. Also, because of the gap in the
adhesive layer 440, the portion of the calibration layer immediately to the right of
the reduced strength portion 480 will tend to remain attached to the shield holder
while the portion of the calibration layer 470 adjacent the tab and located beneath the
gap in the adhesive layer 440 will pull upward and away from the shield holder. This
will cause the calibration layer 470 to begin to tear along the reduced strength
portion 480. As the user continues to pull on the tab 472, the tearing of the
calibration layer 470 will tend to continue across the center portion 474 having the
optical properties used to perform a calibration operation.
If a liquid, gel or paste adhesive is used to attach the calibration layer 470 to
a shield holder 110, there will not be varying adhesive strengths. However, in such
an embodiment it would be advantageous if the adhesive had a greater affinity for the
calibration layer 470 than for the shield holder 110. In this case, most, if not all, of
the adhesive would remain attached to the calibration layer 470 as it is removed from
the shield holder 110. Thus, no adhesive remaining on the shield holder 110 would
contact the skin of a patient or a surface to be measured when the instrument and
attached shield holder 110 are used to take a measurement.
Similarly, if some type of mechanical attachment mechanism is used to attach
the calibration layer 470 to a shield holder 110, it may be advantageous if the
mechanical attachment mechanism is more firmly attached to the calibration layer
470 than to the shield holder 110. This would result in the attachment mechanism
being removed from the shield holder along with the calibration layer, leaving the
shield holder 110 free of any protrusions when used to take a measurement. For
instance, in the embodiment shown in Figure 17, the pins 220 attaching the
calibration target 206 to the shield holder 110 could be more firmly attached to the
calibration target than the shield holder 110. The cylindrical shafts of the pins 220
would extend through the annular portion 112 of the shield holder 110. Ends of the
pins 220 that protrude out the back side of the annular portion 112 could have a
slightly enlarged diameter, thus holding the pins 220 and the attached calibration
target 206 firmly to the shield holder 110. When the user pulls the calibration target
206 away from the shield holder 110, the pins 220 will pull out of the holes in the
annular portion 112. Also, by arranging the pins in a particular orientation with
respect to the user graspable tab 202 of the calibration target 206, the calibration
target can be caused to tear or separate in a predetermined manner.
Once a calibration layer 470 has been completely removed from a shield
holder, the central portion 474 of the calibration layer 470 should be irrevocably
damaged so that the calibration layer 470 cannot be re-used for a new calibration
operation. In the embodiment shown in Figure 5B, because the side of the adhesive
layer 440 in contact with the calibration layer 470 has a greater adhesive strength than
the side 442 which was attached to the shield holder, all of the adhesive layer should
remain attached to the calibration target and be removed from the shield holder
along with the calibration layer 470.
As mentioned above, the calibration target shown in Figure 8 is intended to
be used with a shield holder 110 as shown in Figure 5B. This type of shield holder
110 includes its own integral infection/contamination shield 204.
In an alternate embodiment, as shown in Figure 9, both a calibration target
and an infection/contamination shield are attached to the exterior of a shield holder.
In this embodiment, a first double-sided adhesive layer 410 is attached to a front edge
112 of a shield holder 110, like the one shown in Figure 5A. The opposite side of the
adhesive layer 410 is then attached to a infection/contamination shield 420. In a
preferred embodiment, the infection/contamination shield 420 is substantially
transparent. An adhesive layer 440 and a calibration layer 470 are then attached to
the infection shield 420. The adhesive layer 440 and the calibration layer 470 have
generally the same properties as those described for the embodiment shown in Figure
8. That is, a first side 442 of the adhesive layer 440 has a relatively low adhesive
strength, and the opposite side of the adhesive layer, which is attached to the
calibration layer 470, has a greater adhesive strength. Thus, when a user pulls the tab
472 of the calibration layer 470 and removes the calibration layer, both the
calibration layer and the adhesive layer 440 are removed. This leaves just the
infection/contamination shield 420 attached to the shield holder 110 and the
instrument 100. Of course the double-sided adhesive layers 410 and 440 could also
be replaced with a liquid, gel or paste adhesive, or with a mechanical attachment
device, as described above.
Once a calibration/reference operation has been conducted, and the
calibration target is removed, the instrument can be used to conduct a measurement
on a patient or an object. In one embodiment, light generated by the instrument
passes through the infection shield 420, strikes the patient or object, and is reflected
back through the infection shield 420 to a detector of the device. In an alternate
embodiment, light generated by the instrument would pass through the infection
shield 420, strike the patient or object, and the target patient or object would emit
fluorescent or phosphorescent emissions in response to the emitted light. The
fluorescent or phosphorescent emissions would pass back through the infection
shield and would be detected by the instrument. After a patient or object
measurement has been completed, the shield holder 110 and the attached infection
shield 420 are removed from the instrument 100 and disposed of.
The calibration layer 470 can have a reduced strength portion 480 configured
in many different ways. In the embodiments shown in Figures 8 and 9, the reduced
strength portion extends from a peripheral edge towards a center 474 of the
calibration layer 470. This encourages the calibration layer to tear across the center
portion 474, which is the portion having optical properties used to calibrate a
measuring instrument. In preferred embodiments, the reduced strength portion 480
does not extend beyond the annular radial width of the adhesive layer 480 so that
light cannot penetrate through the calibration layer 470 and affect a calibration or
reference operation.
In the embodiment shown in Figure 10, a calibration target 270 can be
manufactured with two user graspable tabs at its sides. Here, two pull tabs 531 and
533 are attached to two halves 535 and 537 of the calibration target 270. Between the
two halves 535 and 537 is a mechanical perforation 539. When the calibration target
270 is pulled away from a structure of the calibration device by one of the tabs, it
breaks along perforation 539, thereby making it difficult or impossible to reuse. The
remaining half of the calibration target 270 can then be pulled away using the
remaining tab.
In other alternate embodiments, as shown in Figures 11 and 12, the reduced
strength portion can have different configurations. In the embodiment shown in
Figure 11, the reduced strength portion 480 traverses a path across the central region
474 of the calibration layer 470. In the embodiment shown in Figure 12, the reduced
strength portion 480 proceeds in a direct line across the center 474 of the calibration
layer 470. Each of these embodiments is intended to ensure that as the calibration
layer 470 is removed, the central portion 474 used to calibrate the instrument is
altered in a destructive manner so that the calibration layer cannot be reused.
In still other embodiments, a cutting device could be incorporated into the
calibration layer 470, or into the shield holder 110 or the instrument itself. One such
embodiment is shown in Figure 16, where a wire or monofilament 478 is attached to
or embedded in the calibration layer 470. The wire or monofilament 478 will cause
the calibration layer 470 to tear in a predetermined manner when a user pulls on the
tab 472. Although Figure 11 shows the wire or monofilament extending only
partway across the calibration layer 470, the wire or monofilament could extend
further or completely across the calibration layer 470. The wire or monofilament
could also be arranged in a pattern, like the reduced strength portion 474 shown in
Figure 11.
In alternate embodiments, a wire or monofilament could also be attached to
the shield holder. In the embodiment shown in Figure 18, a wire or monofilament
230 is stretched across the back of the calibration layer 200, with ends of the wire or
monofilament being attached to the shield holder 110. Also, the wire or
monofilament 230 could be replaced with any other type of cutting device that will
cause the calibration layer 470 to tear or separate in a predetermined manner when
being removed from a measuring instrument.
If the measuring instrument 100 embodying the invention is configured so that
only a single patient or object measurement may be conducted after each calibration
operation, use of the calibration device can help to prevent patient infection or
patient or object cross-contamination.
When a user attempts to use the measuring instrument, a shield holder with
an infection/contamination shield and a calibration target will first be attached to the
instrument. Next, a calibration/reference operation will be performed. Once the
calibration/reference operation is complete, the user will grasp a tab on the
calibration target and pull on the tab to remove the calibration target. This will cause
the calibration target and any attached adhesive layer to be removed from the shield
holder. The act of removing the calibration target will destroy at least the portion
of the calibration target having the optical properties used to calibrate/reference the
instrument. Thus, it will be impossible to reuse the calibration target. The user
would then proceed to conduct a patient or object measurement with the shield
holder and infection shield still attached to the instrument. The results of the
measurement can then be noted or recorded.
Because the instrument will not perform a second patient or object
measurement without first performing another calibration/reference operation, the
user will be forced to remove both the shield holder and the infection shield and
replace it with a new device that includes a new calibration target. The user will be
forced to perform another calibration operation before the device can be used to
perform another patient or object measurement. For this reason, it should be
impossible for the device to be used to take two measurements on two different
patients or objects using the same shield holder and infection/contamination shield.
This prevents cross-contamination between different patients or objects.
Also, an interlock mechanism in the measuring instrument may interact with
a shield holder to inform the instrument when a shield holder is removed. The
instrument can then be configured so that no patient or object measurements can be
performed once a shield holder has been removed from the instrument. This should
discourage users from attempting to conduct a measurement without an
infection/contamination shield in place, thereby reducing the opportunity for patient
or object cross-contamination. Similarly, the interlock mechanism could be
configured to prevent more than one patient or object measurement cycle from being
performed before a shield holder is removed and another one is inserted.
In a preferred embodiment of the invention, the shield holder is configured as
shown in Figure 5A, and a combined infection/contamination shield and calibration
target 200 will be constructed as shown in Figure 14. In this embodiment, a first
double-sided adhesive layer 410 is used to attach the combined
infection/contamination shield and calibration target to the shield holder 110. The
opposite side of the double-sided adhesive layer 410 is adhered to a shield layer 420.
Next, a clear release liner 430 is attached to the infection/contamination shield 420.
The release liner 430 will remain permanently attached to the infection shield 420,
but will provide a controlled release of the remaining portions of the combined
infection shield and calibration target.
Next, a second double-sided adhesive layer 440 is attached to the release liner
430. As in the previous embodiments, a gap is formed in the adhesive layer 440.
Next, a spacer layer 450 is attached to the opposite side of the second adhesive layer
440. The spacer layer 450 serves to space a calibration layer a precise distance from
an emitting end of an instrument to which the device is attached. A third double-
sided adhesive layer 460 then attaches a calibration layer 470 to the spacer layer 450.
The double sided adhesive layers 410, 440 and 460 could all be replaced with
a liquid, gel or paste adhesive, or by a mechanical attachment device, as explained
above.
The central portion 474 of the calibration layer 470 will be exposed to light
emitted by an emission end of an instrument to which the device is attached. Also,
reduced strength portions are formed in the spacer layer 450, the third double-sided
adhesive layer 460 and the calibration layer 470. As explained above, the reduced
strength portions cause the calibration layer 470 to tear in a predetermined manner
when the calibration layer 470 is removed from the remaining portions of the device.
Also, the reduced strength portions are oriented in a predetermined manner with
respect to the gap in the second double-sided adhesive layer 440. Preferably, the
reduced strength portions are positioned adjacent one side of the gap. When the
device is oriented in this manner, pulling on the tab 472 of the calibration layer 470
causes the calibration layer to tear along the reduced strength portion 480 and to
irrevocably damage the central portion 474 of the calibration layer 470.
Of course, the reduced strength portions could also be replaced by a cutting
device, as explained above, to cause the calibration layer to tear or separate in a
predetermined manner.
In alternate embodiments, the shield holder could be configured as shown in
Figure 13. In this embodiment, the narrower portion of the shield holder is to be
attached to a measuring instrument, and the larger diameter flared portion 112
extends away from the device. A flexible annular ring of material 210 on the rear of
the shield holder may engage projections on the nose portion of a measuring
instrument. In this embodiment, a combined infection/contamination shield and
calibration target 200 is located adjacent the back side 208 of the shield holder 110,
instead of being located on the front end 112. The combined
infection/contamination shield and calibration target 200 still includes a user
graspable tab 202 which can be pulled to remove the calibration target. This
embodiment, like the embodiment shown in Figure 5B, could have an infection
shield mounted on the shield holder and a separate calibration target which is adhered
to the shield holder or the infection/contamination shield.
Another alternate embodiment of a calibration/reference device is shown in
Figures 15A and 15B. In this embodiment, a calibration target holder 125 has a cup¬
like shape. A calibration target 126 may be mounted on the inside of the holder 125,
as shown in Figure 15A. Alternatively, if the holder 125 is transparent, the
calibration target 126 could be mounted on the outside of the holder 125. The holder
125 could be formed of any rigid or semi-rigid material. In a preferred embodiment,
the holder 125 would be made of molded plastic. The calibration target 126 could be
pre-mounted on the holder 125, such that the entire assembly can be used for a
period of time, then discarded. Alternatively, the calibration target 126 could be
removably mounted on the holder 125, such that the holder 125 can be re-used
multiple times with different calibration targets 126. In this instance, the calibration
target 126 could include a user graspable tab 127 that aids removal of the calibration
target 126 from the holder 125.
To use this type of calibration device, the user would place the calibration
device over the detector of a measuring instrument. For instance, the calibration
device could be placed over the nose of a measuring instrument. The measuring
instrument would then conduct a calibration operation using a portion of the
calibration target 126 having known optical properties. The user would then remove
the calibration device from the measuring instrument and conduct a measurement on
a target object or tissue.
An embodiment like the one shown in Figures 15A and 15B could be used
with a measuring device that does not require a calibration operation to be performed
prior to each measurement. This embodiment could be used for periodic calibration
of a measuring device. The holder would ensure that the calibration target is
correctly positioned relative to the light source and detector of the measuring
instrument. Also, the sidewalls of the holder 125 would serve to block outside light
from reaching a detector of the device, thereby ensuring the calibration operation is
accurate.
In a preferred embodiment of the device, the calibration target 126 would be
removably mounted on the holder 125. The user would obtain a calibration target
126 and first place the calibration target 126 on the inside of the holder 125. The user
would then conduct a calibration operation as described above. After the calibration
operation has been performed, the user could remove the calibration target 126 from
the holder 125 using the user graspable tab 127, so that the holder can be re-used with
another calibration target 126.
Either of the calibration targets shown in Figures 8 and 9 could be used with
the holder 125 shown in Figures 15A and 15B. If the calibration target shown in
Figure 8 is used, the double sided adhesive layer 440 could be used to attach the
calibration layer 470 to the inside of the holder 125. In this instance, the calibration
layer 470 would have known optical properties on the side of the calibration layer
470 opposite the adhesive layer 440, which is the side that would face the detector of
a measuring instrument.
If the calibration target shown in Figure 9 is used, an additional adhesive layer
on the side of the calibration layer 470 opposite the adhesive layer 440 could be used
to attach the calibration device to the holder 125. In this instance, when the holder
is placed over the output end of the measuring instrument, the double sided adhesive
layer 410 would be pressed against and adhere to the measuring instrument. Then,
after a calibration operation has been performed, when the holder 125 is removed
from the measuring instrument, it will leave the entire calibration target attached to
the measuring instrument. The user would then remove the calibration layer 470,
and its attached adhesive layer 440, so that the shield layer 420 and the double sided
adhesive layer 410 remain attached to the measuring instrument. The instrument
could then be used to conduct measurements, and the shield layer 420 would act as
a contamination or infection shield. Also, in alternative embodiments, the adhesive
strength of the adhesive layers could be designed such that removal of the cover 125
from the measuring instrument, after a calibration operation, will cause the
calibration layer 470 and adhesive layer 440 to also be removed from the measuring
instrument. This would leave the measuring instrument, with the shield layer 420
and adhesive layer 410, ready to perform a measurement operation. The user could
then remove the calibration layer 470 from the holder 125 so that the holder 125 can
be re-used. Alternatively, the holder 125 and the attached calibration layer 470 and
adhesive layer 440 could simply be discarded.
Also, the portion of a calibration/reference target having known optical
properties need not be simply reflective. In an alternate embodiment, a target layer
of a calibration device embodying the invention could include a fluorescent portion
which emits fluorescent electromagnetic radiation in response to an excitation light.
An embodiment of a fluorescent calibration layer is shown in Figure 19. In this
embodiment, a fluorescent portion 473 is centered on the calibration layer 470.
When a calibration device that includes a fluorescent calibration layer is
attached to a measuring instrument, light from a light source of the measuring
instrument can be used to excite the fluorescent portion 473. The fluorescent
portion 473 would then emit fluorescent electromagnetic radiation, which can be
detected by a detector of the measuring instrument. The fluorescent light emitted by
the fluorescent portion 473 may be at a different wavelength than the light used to
excite the emissions. Thus, a fluorescent calibration device can be used to calibrate
an instrument for light emissions in a different portion of the spectrum than would
be possible with a reflective calibration device.
Also, a calibration/reference operation performed with a fluorescent
calibration/reference target could be designed to determine time characteristics of the
fluorescent target. For instance, the fluorescent target could be illuminated with a
relatively short duration burst of excitation light, then the fluorescent emissions from
the fluorescent target could be monitored to determine the amount of time that
elapses before an amplitude of the fluorescent emissions decay below a threshold
value. The details of such a method are provided in U.S. Patent No. 5,348,018 to
Alfano et al, the contents of which are hereby incorporated by reference.
In an alternate method of conducting a calibration/reference operation with
a fluorescent target, the fluorescent target could be illuminated with an amplitude
modulated beam of excitation light. Because an amplitude of the excitation light
modulates with time, an amplitude of the fluorescent light would also modulate with
time. A detector of a measuring instrument could monitor the fluorescent light
generated by the fluorescent target and compare the amplitude modulation of the
fluorescent light with the amplitude modulation of the excitation light. A phase shift
between the excitation light and fluorescent light provides an indication of the time
characteristics of the fluorescent target. Also, a demodulation factor, which
represents a ratio of the amplitudes of the excitation light to the amplitudes of the
fluorescent light could be used, in conjunction with the phase shift, to determine
properties of the fluorescent calibration device. Details of such a method are
provided in U.S. Patent No. 5,628,310 to Rao et al., the contents of which are hereby
incorporated by reference.
In still other methods of using a fluorescent calibration/reference target,
polarization characteristics of fluorescent light generated by the target, with respect
to a polarization of the excitation light, can be used to determine time characteristics
of the fluorescent target. In this method, a polarized excitation light would
illuminate the fluorescent target. The detector mechanism of the measuring
instrument would be configured to determine polarization characteristics of
fluorescent light output by the fluorescent target in response to the excitation light.
The polarization characteristics of the fluorescent light, with respect to the
polarization of the excitation light could also be used to determine time
characteristics of the fluorescent target. Details of such a method are provided in
U.S. Patent No. 5,515,864 to Zuckerman, the contents of which are hereby
incorporated by reference.
In yet another embodiment, as shown in Figure 20, a calibration layer 470
includes a central region having a fluorescent portion 473 and a portion 474 having
known scattering/reflection properties. When a calibration device including a
calibration layer as shown in Figure 20 is mounted on a measuring instrument, light
emitted from a light source of the instrument can both scatter/reflect off the portion
474 having known properties, and the light can excite fluorescent emissions from the
fluorescent portion 473. The scattered or reflected light, and fluorescent emissions
from the fluorescent portion 473 can be detected by a detector of the measuring
instrument and used to calibrate or reference the instrument.
In still another embodiment, as shown in Figure 21, a fluorescent portion 473
may be centered within a region 474 having known scattering/reflective properties.
Alternatively, the portion having known scattering/reflective properties could be
centered in a larger fluorescent portion. When a target layer 470, as shown in Figure
21, is incorporated in a calibration device embodying the invention, both light
scattered by the portion 474 and fluorescent light emitted by the fluorescent region
473 can be used in a calibration or reference operation.
The two portion calibration layers 470 shown in Figures 20 and 21 allow for
a calibration operation to rely on light having different wavelengths. The light
reflected from the portion 474 having known optical properties will be at the same
wavelength as the light emitted by the measuring instrument. Fluorescent light
generated by the fluorescent portion 473 will be at a different wavelength. This type
of calibration/reference operation could be particularly useful for measuring
instruments that utilize light at more than one wavelength to conduct a measurement
operation. This type of calibration/reference operation could also be useful for a
device that utilizes both fluorescent light generated by a target object, and light that
is scattered or reflected from the target object to conduct a measurement operation.
Also, even when a calibration target having a fluorescent portion is used, by
selectively receiving only the same wavelengths that were emitted by the measuring
instrument, one can conduct a calibration based on scattered light. By selectively
receiving only the wavelengths corresponding to fluorescent light generated by a
target, one can conduct a calibration operation based only on the fluorescent light,
thereby preventing reflectance/scattering properties of the target from affecting the
calibration operation.
Each of the methods of measuring fluorescent radiation described above could
also be used by a measuring system embodying the invention to measure fluorescent
light that is generated by a target object or a target tissue of a patient. For instance,
after a calibration or reference operation has been conducted with a fluorescent
calibration target, the calibration target would be removed, leaving a structure of the
calibration device attached to the measuring instrument. The measuring instrument
could then be used to excite and measure fluorescent radiation from a target object
or tissue. In a preferred embodiment, excitation light from the measuring instrument
would be used to excite fluorescent emissions from a target object or tissue. The
fluorescent emissions would pass through the structure of the calibration device that
remains on the instrument, to a detector of the instrument, which measures the
fluorescent emissions. Such a target object or tissue measurement could be conducted
by using the burst and monitor method, the phase shift method, or the polarization
sensing method.
In a method embodying the invention, the measuring instrument first takes
readings against a reference target, then takes readings against the skin of a patient or
the surface of an object. The patient or object readings are then compared with the
reference target readings to provide a meaningful output value. This output value
may be expressed as an optical density (OD). A formula for calculating an optical
density in a method embodying the invention is shown below in Equation (1).
OD = - Log10 (Skin - SkinDark); (1)
(Ref - RefDark)s
In a method embodying the invention, the measuring instrument is used with
the reference target to obtain two values. First, a reading is taken against the
reference target with a light source of the instrument turned off. This is referred to
as a dark reference reading, which is abbreviated as RefDark in Equation (1). Next,
a reading is taken on the reference target with a light source of the measuring
instrument turned on. This is referred to as a reference reading, which is abbreviated
Ref in Equation (1). Both of these measurements would typically be conducted at a
particular wavelength.
Next, two readings are taken on a patient's skin or on an object. The first
reading is taken with the light source turned off to provide a dark skin reading. This
is abbreviated SkinDark in Equation (1). Next, a reading is taken against the skin of
the patient or on the object with the light source of the measuring instrument turned
on to obtain a patient/object reading. This is abbreviated Skin in Equation (1). The
dark skin reading is then subtracted from the skin reading to provide a corrected
patient/object reading. The dark reference reading is also subtracted from the
normal reference reading to provide a corrected reference reading. A negative
logarithm is then taken of the ratio of the corrected patient reading to the corrected
reference reading. This provides an optical density value which can be used to
diagnose a condition of the patient.
In alternate methods embodying the invention, a plurality of dark skin
readings and normal skin readings may be conducted at multiple different locations
on a patient's skin. The difference between the normal skin reading and the dark
skin reading at each of the different locations can then be averaged to provide the
value for the numerator of Equation (1).
Furthermore, in alternative methods embodying the invention, two or more
patient readings may be conducted at different wavelengths, and the results of each
of the readings may provide a plurality of different optical density values that are
then combined to determine a condition of the patient.
Still further, both the skin and reference readings described above may be
corrected for "stray light." Theoretically, there is no light with a wavelength lower
than 350 nm or with a wavelength higher than 850 nm. Signal levels detected at such
wavelengths are considered "stray light." A method for correcting for stray light is
described below with reference to Equation (2).
(I(λ))s = (I(λ) - [1(330) - 1(330) - 1(900) (λ-330)] (2)
(900-300)
If I(λ) represents a corrected skin reading or a corrected reference reading, as
described above, these readings can be corrected for stray light using Equation (2)
shown above. The correction for stray light requires that the intensity of light be
measured at 330 nm to provide a value 1(330), and that the intensity of light at 900
nm be measured to provide a value 1(900). These values are then inserted in Equation
(2), shown above, to provide a stray light corrected intensity value (I(λ))s. These stray
light corrected intensity values for the corrected skin intensity and the corrected
reference intensities are used in Equation (1) above to provide an optical density value
which can be used to diagnose a condition of a patient.
Furthermore, a measuring system embodying the invention could be
configured to measure light from a target object or tissue at more than one
wavelength. For instance, in embodiments where light from the measuring
instrument illuminates the target object or tissue and is scattered or reflected back to
the measuring instrument, a detector of the instrument could measure the reflected
or scattered light at multiple wavelengths.
In still other embodiments of the invention, the target layer 470 of a
calibration target could be partially transmissive so that light transmitted through the
target layer can be used to perform a calibration or reference operation. For instance,
in the embodiment shown in Figure 8, the central region could have known
transmissive properties so that light transmitted through the central region 474 may
be used to perform a calibration or reference operation. Two methods for
performing a calibration or reference operation using a transmissive calibration target
will now be described with reference to Figures 22, 23, 24 A ad 24B.
Figure 22 shows an external light source that can be used to perform a
transmissive calibration or reference operation, and to conduct a transmissive
measuring operation. The external light source 240 includes a light source 242, which
can be in the form of an incandescent or fluorescent bulb, a light emitting diode, a
laser, or any other device capable of generating electromagnetic radiation. An
aperture 244 allows light from the light source 242 to escape the device. A slot 246,
or any other type of mechanical attachment mechanism, can be used to mount a
sample to be measured in the aperture 244 of the light source 240.
Figure 23 shows a measuring instrument 100 being used to conduct a
calibration or measurement operation using the external light source 240. If a
calibration operation is to be performed, the light source 242 is turned on, and a
calibration or reference device is mounted on the measuring instrument 100. The
calibration device would include a calibration/reference target mounted on a shield
holder 110. The calibration device is then pressed against the aperture 244 of the
external light source 240. Light from the light source 242 passes through the
aperture, and a portion of the light also passes through the calibration device. The
light transmitted through the calibration device is received by a detector within the
measuring instrument 100 and is used to conduct a calibration or reference operation.
In some embodiments of the device, a clear window 248 may be mounted in the
aperture 244, and the calibration target may be pressed directly against the window
248.
Once a calibration or reference operation has been successfully performed, the
calibration layer of the calibration device would be removed so that the device is
ready to conduct a patient or object measurement. Removal of the calibration device
could leave a shield holder 110 and an associated infection shield attached to the
measuring instrument 100. An object to be measured may then be mounted on a
slide 248 that is inserted into the aperture 244 of the external light source 240. The
shield holder 110, without the calibration target, would then be pressed against the
slide 248, and the measurement device would be activated to conduct a measurement.
Light from the light source 242 would pass through the slide 248, the sample
mounted thereon, and the infection shield and shield holder 110, and the transmitted
hght would be detected by a detector of the measuring instrument 100. The
transmitted light would then be used to conduct a measurement operation.
This type of an embodiment could be useful for measuring optical properties
or colors of objects capable of being mounted on slides 248 that are inserted into an
external light source 240. In alternate embodiments, the measurement operation
could be performed directly on an object without the use of the external light source
240. In this embodiment, the external light source 240 would be used only to
perform a calibration or reference operation with a transmissive calibration target.
In the embodiment shown in Figures 24A and 24B, a light source of the
measuring instrument would be used to conduct a transmissive calibration and/or
measuring operation. The measuring instrument 100 would include a means for
applying light to a calibration/reference target mounted on the instrument 100. The
means could include a light source inside the instrument 100 which transmits light
through an optical fiber to a light head 251. In alternate embodiments, the light head
251 could include an integral light source. In either event, the light head 251 may be
attached to a retractable tether 252 for holding the light head 251 in place on top of
the instrument 100 when it is not in use. If an optical fiber is used to conduct light
from a source inside the instrument to the light head 251, the optical fiber could be
inside the tether 252.
With an embodiment like the one shown in Figures 24 A and 24B, a shield
holder 110 and an attached transmissive calibration target would be mounted on a
nose portion 104 of the measuring instrument 100. Next, the retractable light head
251 would be pulled out of the device and placed over the transmissive calibration
target attached to the shield holder 110. The device would then be activated so that
light is emitted from the light head 251, is transmitted through the transmissive
target, and is detected by a detector of the instrument 100 so that a
calibration/reference operation may be performed.
Once a calibration/reference operation has been performed, the light head 251
could then be retracted back into the measuring instrument, and the calibration
target would be removed from the shield holder 110. This would place the
instrument in a condition ready for a patient or object measurement. The
measurement operation could be conducted such that light emitted from the nose
portion 104 of the instrument is reflected/scattered from the target object and is
detected by the instrument. Alternatively, the light head 251 could be used to
provide light for a measurement operation.
In some of the embodiments described above, a calibration operation has
relied on light that is reflected/scattered from, transmitted through or emitted by, a
portion of a calibration target having known optical properties. This could involve
determining an amplitude of the reflected/scattered/transmitted/emitted light at one
or more wavelengths. In other devices and methods embodying the invention, the
radiation output to the calibration target could have a particular polarization
orientation. The measuring instrument could then be configured to determine a
polarization orientation of the reflected/scattered/transmitted/emitted light. Such
a method could rely on the relative attenuation of a polarized or depolarized
component of reflected/scattered/transmitted light, or an extent of depolarization.
Many variations could be made to the embodiments of the calibration targets
described above without departing from the spirit or scope of the present invention.
For instance, although each of the embodiments shown in the drawing figures have
a shield holder and a calibration/reference target that is generally circular or annular
in shape, any other shape could be used without departing from the invention. For
instance, the shield holder, infection shield and calibration target could be
rectangular, square, or any other shape necessary to conform to the shape of the
instrument to which the device is attached.
Also, the calibration layers of the embodiments described above could have
any type of optical, transmissive or fluorescent properties used to conduct a
calibration or reference operation. As mentioned above, use of the term "calibration
target" in the specification and claims is intended to encompass both calibration
targets and reference targets. Likewise, use of the term "calibration operation" is
intended to encompass both calibration and reference operations.
In any one embodiment of the invention, the calibration layer would have
very specific reflective, transmissive and/or fluorescent properties. However,
calibration/reference targets embodying the invention might include different types
of calibration layers having different reflective/transmissive/fluorescent properties.
For instance, colored calibration targets could be provided in a variety of different
skin tones. A calibration device embodying the invention could then be selected by
a user based on a patient's skin tone or age, and the selected calibration target could
be used to calibrate an instrument.
Also, the reflective/transmissive/fluorescent properties of a calibration target
may be selected such that a measuring instrument can be calibrated/referenced at the
mean or the median of the expected measurement range. Such a strategy will provide
maximum measurement accuracy since any error is at a minimum for measurements
closest to the calibration value. For example, the reflectance of a calibration target
can be formulated such that its reflectance matches the median reflectance of the
patients expected to be measured with the instrument. As an additional example, the
fluorescence lifetime and/or quantum yield of a fluorescent target may be selected
such that it equals the median lifetime and/or quantum yield of the fluorescing
analyte being measured.
Also, although each of the embodiments described above have a user graspable
tab attached to the calibration layer, other types of user graspable tab configurations
are possible. For instance, instead of being a tab, a cord, a string or a ring of material
could be attached to the calibration layer. For instance, in the embodiment shown
in Figure 18, the user graspable tab 202a is a loop of material whose ends are attached
to the calibration layer 200. Each of these items is easy for the finger of a user to
grasp and to pull. The invention is intended to include any type of user graspable
tab, cord, string, ring, or other device that can be used to remove the calibration layer
from the remaining portions of the device.
Furthermore, in the embodiments described above, an infection shield and a
calibration target are attached to a shield holder, which in turn is attached to the
instrument. Some embodiments of the device may not utilize a shield holder. In
these embodiments, the infection shield and/or the calibration target may be directly
attached to a measuring instrument. These embodiments may use an adhesive layer
or a mechanical attachment device to attach the infection shield and the calibration
target to the instrument.
Still further, if the instrument which the device is used with is not used for
medical purposes, and infection or cross-contamination is not an issue, a device
embodying the invention may simply comprise a calibration layer. The calibration
target in Figure 8 provides an example of such an embodiment. This calibration
target could be directly attached to the measuring instrument.
In yet another embodiment of the invention, a plurality of emitter and
detector pairs could be arranged in an array on a measuring instrument. During a
calibration operation using any of the calibration devices described above, the light
output from the emitters could reflect/scatter from or be transmitted through
portions of the calibration device and impinge on the respective detectors. If a
fluorescent calibration target is used, fluorescent light from the target could impinge
on the detectors. After the calibration operation is conducted, the same
emitter/detector pairs could be used to interrogate multiple points on a target
material or tissue. Such a configuration would allow the measuring instrument to
develop an image of the target material or tissue, or an image of
reflective/transmissive/fluorescent properties of the target.
In still other embodiments, one or more light sources could illuminate/excite
a target material or tissue, and reflected/scattered/transmitted light, or fluorescent
light, passing from the target material or tissue could impinge on a detector array
configured generate an image of the material or tissue, or an image of the
reflective/transmissive/fluorescent properties of the target material or tissue. For
instance, a charged coupled device (CCD) could be used as the detector array. The
calibration devices described above could be used to calibrate or reference a
measuring instrument that utilizes such a detector array.
Figures 25A, 25B, and 25C show front, side and back views, respectively, of
a measurement system 803 embodying the invention. Figure 25D shows the
measurement system 803 in a charging stand 871. The elements in the measurement
system 803 which have similar counterparts in the previously discussed system 3, will
also have the earlier reference numbers indicated in parenthesis.
The measurement system 803 includes a housing 843 which is sized so as to
be easily graspable by a human hand. A radiation analyzer 810 is coupled to the
calibration device 845 via one or more optical fibers 833 (see Figure 25B). A
calibration device 845 may be inserted into an opening end 846 of a cone-shaped
holder 858 of the housing 843. A curved portion 866 of the housing 843 allows the
user's hand to comfortably hold the measurement system 803.
Figure 8B shows a side view of the measurement system 803, including the
radiation analyzer 810 and a push button 861. The radiation analyzer 810 is mounted
on a printed circuit board (PCB) 818, which is powered by batteries 822. The
batteries 822 can be recharged when the system 803 is placed in a power adapter stand
through a charger connection 826. A liquid crystal display (LCD) device 832 is also
coupled to the PCB 818. An LCD device 832, which is visible through a window
841, displays measurement results, instructions, warnings, and other operating
information. The radiation analyzer 810 is controlled by a processor also mounted
on PCB 818.
Figures 25C and 25D show a back view of system 803, which includes back
portion 891 and the LCD device 832. A person can initiate a calibration, and then
a measurement, by pressing push button 861 with his or her thumb. In particular,
once a calibration measurement has been performed, the user graspable tab 280 (see
previous figures) is used to peel the calibration target 270 away from the window 260,
and the system 803 is ready to make a measurement on a patient. The LCD device
832 indicates when the measurement system 803 is ready to make a calibration
measurement, when a calibration measurement has been completed and the system
803 is ready to make an actual measurement, and when the system 803 has completed
a measurement. The LCD device 832 also displays the results of measurements, and
messages or other indicators. For instance, the LCD device 832 might show that a
particular calibration target 270 has already been used and that no additional
measurements can be made until a new calibration measurement is made.
A limit switch (not shown) may be installed at the end of the tip 858 to detect
the presence of a calibration device 45. Once the limit switch is engaged, a
calibration measurement is enabled and a measurement counter is initialized to zero.
Calibration is then performed to ready the device for taking a measurement. The
system software then increments the counter each time a measurement is made, up
to a predetermined maximum. Once the maximum number of measurements is
reached, the system software indicates that a calibration is again required, and the
device is prevented from taking additional measurements. Should the limit switch
be disengaged at any time in the measurement sequence, indicating the removal of the
disposable tip, the display indicates that a new calibration sequence must be begun
before other measurements may be taken. These software controls prevent an
operator from using one calibration target more than a predetermined number of
times before replacing the calibration device.
Figure 25D shows a measurement system 803 with a charging stand 871 for
storing and charging the system 803. The charging stand 871 includes a center
portion 873 for receiving the system 803. The center portion 873 serves as both a
stand and a recharging unit. The stand 871 has an electrical cord (not shown) which
can be plugged into an outlet. The stand 871 also includes an electrical receiving unit
which receives charger connection 826 (see Figure 8B) of the system 803. An
indicator light 876 indicates when the measurement system 803 is properly placed in
the center portion 873 so that recharging may take place. The stand 871 further
includes a side receiving portion 875 which can be used to hold a supply 877 of
calibration devices 845.
A measuring instrument embodying the invention to transmit measurement
data directly from the instrument to a recording device via a wireless communication
system. The wireless communication system could be a radio link or infrared
communication link. Similarly, a charger stand for the measurement instrument
could receive measurement data and transmit the measurement data to a recording
device via a communication link.
Figure 26A is a schematic diagram of certain elements of a measurement
system 803, and in particular, of a radiation analyzer instrument 810. The radiation
analyzing instrument 810 includes an optical unit 914, a central processor unit (CPU)
905, and a memory 909. Figure 26B shows a perspective view of an optical unit 914
that includes an optical source 918, a detector array 923, an optical grating 951 and
an output 955 which couples the optical unit 914 to the CPU 905 via a data bus 961.
The optical source 918 may be a tungsten halogen bulb, a noble gas filled tungsten
bulb or several LED's covering the desired regions of the optical spectrum. The
optical source 918 may also be placed at a location in the device housing to
illuminate the subject directly, without coupling the radiation into a fiber.
The embodiment shown in Figure 26B utilizes a microspectrometer offered
by American Laubscher Corporation of Farmingdale, LI, NY called the VIS/NIR
microspectrometer. Optical radiation 940 is output from optical source 918 and is
transmitted via fiber 833 to the target (not shown) to be measured. The return signal
941 travels back down optical fiber 833 and is output from fiber end 958 into a type
of waveguide 962 (cut away) and is incident on diffraction grating 951. Diffraction
grating 951 achieves self-focussing of radiation 941 to different points or detectors on
diode array 923, depending on the intensity and wavelengths of the return radiation
941.
The operation of system 803 will now be described in conjunction with
Figures 26A and 26B. First, a calibration target starts out being arranged on a
window of the measuring system, and a user pushes a button, which indicates that
a calibration measurement should be taken. Radiation 940 is emitted toward the
calibration target, which reflects at least a portion of the radiation back to the
measurement system. Because the calibration target has a known spectral
characteristic, the returned radiation 941 results in a detected intensity at individual
detectors on the detector array 923, thereby yielding a measured calibration
characteristic. This measured calibration characteristic is compared to the expected
or known spectral characteristic of the calibration target, and a resulting adjustment
value (which could be an array of values) is determined. The calibration target is
then removed, and a measurement of tissue or material is made by outputting
radiation 940 as above. A resulting spectral characteristic is then output from
detector array 923, which in turn is adjusted by CPU 905 using the adjustment value
or characteristic to yield a calibrated spectral characteristic. The calibrated spectral
characteristic can then be used to determine some measurable characteristic of the
material or tissue. One such measurement is a non-intrusive bilirubin measurement
according to one embodiment of the invention, as will be discussed below.
Although a microspectrometer as shown in Figure 26B may be used in an
embodiment of the invention, other devices capable of measuring the amplitude of
radiation reflected from a patient's skin at different wavelengths can also be used.
For instance, Figure 31 shows a radiation analyzing device that includes a processor
905, a radiation source 918, radiation conduits 833, such as optical fibers, a memory
909 and a filter/detector unit 1000. The filter/detector unit may comprise a plurality
of detectors and filters. For instance, filters 1, 2 and 3 1010, 1020 and 1030, may be
designed to pass only discreet wavelengths of the radiation reflected from a patient's
skin. Each of the filters may be paired with a corresponding detector to determine
the amplitude of light reflected from a patient's skin at each of the three filter
wavelengths. Alternatively, the filters may be successively coupled to a single
detector to determine the amplitude of the reflected light at each of the filter
wavelengths. In yet another embodiment, the filter/detector unit 1000 may comprise
a detector with a linear variable filter.
If the radiation conduits 833 of the device shown in Figure 31 comprise optical
fibers, the numerical aperture of the optical fibers can be selected to optimize the
efficiency of the device. For instance, the optical fibers used to transmit radiation
from the radiation source 918 to the patient's skin may have a numerical aperture
matched to the radiation source 918. In addition, the optical fibers used to transmit
light reflected from the patient's skin to the radiation analyzer may have a numerical
aperture matched to the radiation analyzer.
The optical fiber 833 of measurement device 803 may comprise one or a
plurality of fibers. Preferably, the optical fiber 833 comprises a plurality of fibers
arranged in a bundle. Figure 27 shows a bundle of optical fibers 333 which can be
used to transmit and receive radiation. The optical fibers are arranged so that they
approach a surface of a material or tissue 40 to be measured at an angle θ relative to
an axis perpendicular to the surface of the material or tissue 40. When the bundle of
optical fibers is inclined in this manner, backscattering effects are reduced. Angle θ
is preferably not 0° and sufficiently large to prevent backscattering effects. In one
embodiment, angle θ is between a few degrees and 20° and preferably between 5° and
10° and more preferably approximately 7°.
Figure 28 shows the bundle of optical fibers 333 as seen from section line 28-28
of Figure 27. In the bundle of optical fibers 333, there is an outer ring of transmission
optical fibers 336, an inner ring of transmission fibers 337 and a central receive
optical fiber 335. When the device is in operation, radiation is transmitted through
the first and second rings of transmission fibers 336, 337, is reflected off the skin of
a patient, and received by the receive optical fiber 335.
Figure 29 shows the bundle of optical fibers as seen from section line 29-29 of
Figure 27. Because the ends of the optical fibers are cut at a slight angle, and because
the optical fibers themselves are cylindrical, the ends of the optical fibers appear to
be ovals in Figure 29.
Figure 30 shows a receive optical fiber 335 and four transmit optical fibers 336
and 337 surrounding the receive optical fiber 335. The receive optical fiber has a
smaller numerical aperture than the transmit optical fibers. The lines extending
down from the bottom of the optical fibers show the path that radiation would take
to leave or enter the optical fibers. For instance the area 335A shows the path that
radiation may take to enter the receive optical fiber 335. The areas marked 336A and
337A show the path that radiation may take when leaving a transmit optical fiber 336
and 337. Typically, the numerical aperture of the receive optical fiber 335 will be
smaller than the numerical aperture of the transmit optical fibers 336 and 337.
Bilirubin Measurement Process
U.S. Patent No. 5,353,790, the contents of which are incorporated herein by
reference, presents a method and apparatus for determining bilirubin concentration
in human tissue such as skin. In particular, the patent discusses reflecting light from
the skin of a patient to determine a bilirubin concentration. The approach corrects
for maturity-dependent optical properties of the skin, including the amount of
melanin in the skin and the amount of blood in the skin. Reflected red to infrared
light is used to determine the maturity-dependent optical properties, reflected red
light is used to determine melanin content, and reflected yellow-orange light is used
to determine the amount of blood in the skin. These quantities are used, in
combination with reflected blue light, to calculate cutaneous bilirubin concentration.
U.S. Patent No. 5,353,790 discusses the absorption spectrum of melanin and
shows that the melanin absorption spectra essentially decreases linearly with
wavelength in the visible region. Moreover, since the melanin absorption varies
orders of magnitudes over the visible region, variations in skin pigmentation will
cause large absolute changes in the absorption at the shorter wavelengths, but the
same magnitude changes will cause relatively minuscule absolute changes in the very
long wavelengths (> 800 nm). The melanin pigmentation measured in the far red
wavelength range was found to have a pivot point at around 637 nm.
A measurement system embodying the invention and configured to detect a
bilirubin concentration in a patient takes advantage of the above phenomena and uses
spectral reflectance to determine a serum bilirubin level in mg/dL (milligrams of
bilirubin per deciliters of blood), as will now be discussed. Figure 32 shows a
flowchart setting forth the steps of a first method embodying the invention that may
be used by a measurement system to perform bilirubin measurements on a patient.
The steps performed are an improved version of the approach discussed in U.S.
Patent No. 5,353,790. Step 702 involves performing a calibration measurement in a
manner similar to that described above. This involves simply outputting radiation
to a calibration target, and measuring the return signal (which could be
reflected/scattered/transmitted/ flourescent light). The calibration measurement
yields a measured calibration spectrum, which is compared to an expected calibration
spectrum (which in turn, depends on the calibration target). The difference between
the expected or known spectrum and the measured spectrum serves as the calibration
data. The calibration data is used to modify actual measured data, thereby
compensating for unit to unit and time varying changes in source luminosity,
delivery optics, collection optics, detection sensitivity, electronic drift, and
environmental conditions such as temperature and humidity.
Step 704 involves making a measurement of a patient's skin by illuminating
the skin with light and detecting a frequency spectrum of light reflected from the
patient's skin. Step 708 involves converting the reflection (scattering) measurements
into an optical density. Step 712 then involves calculating, from a first portion of the
spectrum, a first parameter indicative of a maturity of the skin. Step 716 involves
calculating, from a second portion of the spectrum, a second parameter indicative of
an amount of melanin in the skin. Step 720 involves calculating, from a third portion
of the spectrum, a third parameter indicative of a blood content of the skin. Step 724
involves calculating, from a fourth portion of the spectrum, a fourth parameter
indicative of an uncorrected bilirubin concentration in the skin. Step 728 involves
calculating a corrected bilirubin concentration in the skin as a function of the first,
second, third and fourth parameters.
Figure 33 shows the results of data taken using the method illustrated in Figure
32, versus a standard serum bilirubin (heel stick) method. The subjects were 72 full
term babies of varied ethnic background, with 20 African Americans, 2 Hispanic
Americans, 48 white Americans, and 2 Asian Americans. "R" represents the
correlation coefficient between the measurement method described in Figure 32,
versus the standard method of serum bilirubin. The correlation coefficient shown
is 0.9165 with a perfect correlation given as 1.0000. The tests represent a purely
prospective application of the method illustrated in Figure 32.
Figure 34 shows a flowchart setting forth the steps of another method
embodying the invention for measuring a bilirubin concentration of a patient. This
second method is a more simplified method compared to the method described
above. In step 1805 the measurement system first makes a calibration measurement
as described above. Next, in step 1810, a measurement is made using a first portion
of the spectrum to determine an amplitude of the reflected light at a first wavelength.
Next, in step 1815, a measurement is made at a second portion of the spectrum to
determine an amplitude of light at a second wavelength. The first and second
wavelengths are indicative of the blood content of the patient's skin. In step 1820,
a third measurement is made to determine the amplitude of the reflective light at a
third wavelength indicative of an uncorrected bilirubin score. In step 1825, a CPU
of the measurement device calculates a calibrated and corrected bilirubin
concentration using the results of steps 1805 through 1820.
The significance of making measurements at the first and second wavelengths
will now be explained with reference to Figure 35. Figure 35 illustrates two lines, L3
and L4, that represent the amplitude of light reflected from a patient's skin under two
different conditions. In a first condition, the blood flowing through the patient's
skin is fully oxygenated. In the second condition, the blood flowing through the
patient's skin has no oxygen attached to the hemoglobin in the blood. As shown in
Figure 35, lines L3 and L4 cross one another at two points H and I. Experimental
results have indicated that the wavelengths corresponding to points H and I are at
approximately 526 and 585 nanometers, respectively.
By making the measurements of the amplitude of light reflected from a
patient's skin at approximately 526 nanometers and 586 nanometers, it is possible to
obtain a measurement representative of the blood content of the patient's skin.
Because the measurements are made at the crossover points, it does not matter
whether the blood in the patient's skin is fully or partially oxygenated.
The method of calculating a calibrated and corrected bilirubin concentration
of Figure 34 will now be further explained with reference to Figure 36. In Figure 36,
L5 represents an amplitude of light reflected from a patient's skin at various
wavelengths.
The amplitude of light reflected from a patient's skin at a first wavelength, as
measured in step 1810, is taken at a wavelength of approximately 526 nanometers.
The amplitude at this wavelength is represented by point B in Figure 16. The
amplitude of the light reflected from the patient's skin at the second wavelength is
taken at approximately 586 nanometers, which is represented by point C in Figure
36. An imaginary line Ll is drawn through points B and C and backwards through
smaller wavelengths of the visible light spectrum. The amplitude value at the
intersection of the line Ll and an imaginary line at 476 nanometers is then
determined, which is represented by point D in Figure 36. Point A in Figure 36
represents the measured amplitude of the light reflected from the patient's skin at 476
nanometers. The value of point D is then subtracted from the value of point A to
determine a corrected bilirubin score. This corrected bilirubin score is then used
with the calibration data taken during a calibration measurement to determine a
calibrated and corrected bilirubin concentration of the patient's skin.
The second method described above is far more simple than the first method,
as it only involves taking amplitude measurements of reflected light at three discreet
wavelengths. Experimental results have shown that the second method provides
substantially the same level of accuracy as the first method, and in some cases the
second method produces even better results.
A third method of determining a bilirubin concentration in a patient's skin
will now be described with reference to Figure 37. Figure 37 shows a flowchart of
the steps of a third method of determining a patient's bilirubin concentration. In
step 1905, a calibration measurement is taken as described above. In step 1910,
measurements of the amplitude of light reflected from a patient's skin are made at
first, second, third, fourth and fifth wavelengths. In step 1915, the first, second and
third measurements are adjusted based on the fourth and fifth measurements. In step
1920, a calibrated and corrected bilirubin concentration is calculated using the
calibration measurement and the adjusted first, second and third measurements.
The first, second and third measurements taken during step 1910 are taken at
the wavelengths 486 nanometers, 526 nanometers, and 586 nanometers as described
above in connection with the second method. The fourth and fifth measurements
are taken at wavelengths J and K, as shown in Figure 36, which are represented by
the points M and N. The wavelengths corresponding to J and K are in the range
between 600 and 700 nanometers. The amplitude of the light reflected from the
patient's skin at frequencies J and K are representative of melanin in the patient's
skin. A line drawn through points J and K will have a negative slope that indicates
the amount of melanin in the patient's skin. The greater than negative slope (or the
more steeply the line is inclined down toward the right) the greater the amount of
melanin.
In step 1915, the first, second and third measurements are adjusted based on
the fourth and fifth measurements. To accomplish this adjustment, a line L2 is
drawn through points M and N, and the line L2 is projected backwards through the
smaller wavelengths, as shown in Figure 36. Points of intersection of the line L2
with imaginary lines at the first, second and third wavelengths are determined. These
points are shown as points E, F and G in Figure 36. The amplitude values of points
E, F and G are then subtracted from the respective measurements made at these
wavelengths, which are shown as points C, B and A. These adjusted measurements
for the first, second and third wavelengths are then used to determine a calibrated and
corrected bilirubin concentration for the patient according to the methods described
above.
The above-described process calls for a single measurement to be made on a
single location on a patient's skin. A measuring device embodying the invention
could be configured to take a plurality of measurements on the same portion of the
patient's body, or at different portions of the patient's body and to average the
measurements to create a final measurement result. Also, if a plurality of
measurements are taken, one or more of the measurements having the greatest
deviation may be discarded, and an average of a lesser number of measurements may
be created to arrive at a final measurement result. Further, if the deviation between
a plurality of measurements exceeds a predetermined standard deviation, the entire
set of measurements may be discarded, and a new set of measurements may be
obtained.
Many alternatives and modifications of the above examples would be
apparent to those skilled in the art upon reading the foregoing or practicing the
invention. The apparatus and methods described above are intended to be exemplary
and are not intended to limit the scope of the invention as defined by the following
claims.